US20040011366A1 - System of implantable devices for monitoring and/or affecting body parameters - Google Patents

System of implantable devices for monitoring and/or affecting body parameters Download PDF

Info

Publication number
US20040011366A1
US20040011366A1 US10/391,424 US39142403A US2004011366A1 US 20040011366 A1 US20040011366 A1 US 20040011366A1 US 39142403 A US39142403 A US 39142403A US 2004011366 A1 US2004011366 A1 US 2004011366A1
Authority
US
United States
Prior art keywords
data signal
patient
control unit
signals
command
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Abandoned
Application number
US10/391,424
Inventor
Joseph Schulman
Robert Dell
John Gord
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Alfred E Mann Foundation for Scientific Research
Original Assignee
Individual
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Priority claimed from US09/030,106 external-priority patent/US6185452B1/en
Priority to US10/391,424 priority Critical patent/US20040011366A1/en
Application filed by Individual filed Critical Individual
Priority to US10/719,715 priority patent/US7114502B2/en
Publication of US20040011366A1 publication Critical patent/US20040011366A1/en
Priority to US10/920,570 priority patent/US8555894B2/en
Priority to US10/920,554 priority patent/US8684009B2/en
Priority to US10/997,398 priority patent/US20050075682A1/en
Priority to US11/004,758 priority patent/US7460911B2/en
Priority to US11/187,290 priority patent/US7513257B2/en
Assigned to ALFRED E. MANN FOUNDATION FOR SCIENTIFIC RESEARCH reassignment ALFRED E. MANN FOUNDATION FOR SCIENTIFIC RESEARCH ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: DELL, ROBERT DAN, GORD, JOHN C., SCHULMAN, JOSEPH H.
Priority to US14/197,797 priority patent/US9750428B2/en
Abandoned legal-status Critical Current

Links

Images

Classifications

    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61NELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00Electrotherapy; Circuits therefor
    • A61N1/18Applying electric currents by contact electrodes
    • A61N1/32Applying electric currents by contact electrodes alternating or intermittent currents
    • A61N1/36Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
    • A61N1/372Arrangements in connection with the implantation of stimulators
    • A61N1/37211Means for communicating with stimulators
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00Measuring for diagnostic purposes; Identification of persons
    • A61B5/0002Remote monitoring of patients using telemetry, e.g. transmission of vital signals via a communication network
    • A61B5/0031Implanted circuitry
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00Measuring for diagnostic purposes; Identification of persons
    • A61B5/07Endoradiosondes
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00Measuring for diagnostic purposes; Identification of persons
    • A61B5/45For evaluating or diagnosing the musculoskeletal system or teeth
    • A61B5/4519Muscles
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61NELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00Electrotherapy; Circuits therefor
    • A61N1/18Applying electric currents by contact electrodes
    • A61N1/32Applying electric currents by contact electrodes alternating or intermittent currents
    • A61N1/36Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
    • A61N1/372Arrangements in connection with the implantation of stimulators
    • A61N1/37211Means for communicating with stimulators
    • A61N1/37252Details of algorithms or data aspects of communication system, e.g. handshaking, transmitting specific data or segmenting data
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61NELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00Electrotherapy; Circuits therefor
    • A61N1/18Applying electric currents by contact electrodes
    • A61N1/32Applying electric currents by contact electrodes alternating or intermittent currents
    • A61N1/36Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
    • A61N1/372Arrangements in connection with the implantation of stimulators
    • A61N1/37211Means for communicating with stimulators
    • A61N1/37252Details of algorithms or data aspects of communication system, e.g. handshaking, transmitting specific data or segmenting data
    • A61N1/37288Communication to several implantable medical devices within one patient
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61NELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00Electrotherapy; Circuits therefor
    • A61N1/18Applying electric currents by contact electrodes
    • A61N1/32Applying electric currents by contact electrodes alternating or intermittent currents
    • A61N1/36Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
    • A61N1/372Arrangements in connection with the implantation of stimulators
    • A61N1/378Electrical supply
    • A61N1/3787Electrical supply from an external energy source
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B2560/00Constructional details of operational features of apparatus; Accessories for medical measuring apparatus
    • A61B2560/02Operational features
    • A61B2560/0204Operational features of power management
    • A61B2560/0214Operational features of power management of power generation or supply
    • A61B2560/0219Operational features of power management of power generation or supply of externally powered implanted units
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B2562/00Details of sensors; Constructional details of sensor housings or probes; Accessories for sensors
    • A61B2562/08Sensors provided with means for identification, e.g. barcodes or memory chips
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00Measuring for diagnostic purposes; Identification of persons
    • A61B5/05Detecting, measuring or recording for diagnosis by means of electric currents or magnetic fields; Measuring using microwaves or radio waves 
    • A61B5/053Measuring electrical impedance or conductance of a portion of the body
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00Measuring for diagnostic purposes; Identification of persons
    • A61B5/145Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00Measuring for diagnostic purposes; Identification of persons
    • A61B5/145Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue
    • A61B5/14532Measuring characteristics of blood in vivo, e.g. gas concentration, pH value; Measuring characteristics of body fluids or tissues, e.g. interstitial fluid, cerebral tissue for measuring glucose, e.g. by tissue impedance measurement
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00Measuring for diagnostic purposes; Identification of persons
    • A61B5/45For evaluating or diagnosing the musculoskeletal system or teeth
    • A61B5/4528Joints
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/50Prostheses not implantable in the body
    • A61F2/68Operating or control means
    • A61F2/70Operating or control means electrical
    • A61F2/72Bioelectric control, e.g. myoelectric
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/50Prostheses not implantable in the body
    • A61F2002/5058Prostheses not implantable in the body having means for restoring the perception of senses
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/50Prostheses not implantable in the body
    • A61F2/68Operating or control means
    • A61F2/70Operating or control means electrical
    • A61F2002/704Operating or control means electrical computer-controlled, e.g. robotic control
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61FFILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/50Prostheses not implantable in the body
    • A61F2/68Operating or control means
    • A61F2/70Operating or control means electrical
    • A61F2002/705Electromagnetic data transfer
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61NELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N1/00Electrotherapy; Circuits therefor
    • A61N1/18Applying electric currents by contact electrodes
    • A61N1/32Applying electric currents by contact electrodes alternating or intermittent currents
    • A61N1/36Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
    • A61N1/372Arrangements in connection with the implantation of stimulators
    • A61N1/37205Microstimulators, e.g. implantable through a cannula

Definitions

  • the present invention relates to systems for monitoring and/or affecting parameters of a patient's body for the purpose of medical diagnosis and/or treatment. More particularly, systems in accordance with the invention are characterized by a plurality of devices, preferably battery-powered, configured for implanting within a patient's body, each device being configured to sense a body parameter, e.g., temperature, O 2 content, physical position, etc., and/or to affect a parameter, e.g., via nerve stimulation.
  • a body parameter e.g., temperature, O 2 content, physical position, etc.
  • the present invention is directed to a system for monitoring and/or affecting parameters of a patient's body and more particularly to such a system comprised of a system control unit (SCU) and one or more devices implanted in the patient's body, i.e., within the envelope defined by the patient's skin.
  • SCU system control unit
  • Each said implanted device is configured to be monitored and/or controlled by the SCU via a wireless communication channel.
  • the SCU comprises a programmable unit capable of (1) transmitting commands to at least some of a plurality of implanted devices and (2) receiving data signals from at least some of those implanted devices.
  • the system operates in closed loop fashion whereby the commands transmitted by the SCU are dependent, in part, on the content of the data signals received by the SCU.
  • each implanted device is configured similarly to the devices described in Applicants' parent application Ser. No. ______, and typically comprises a sealed housing suitable for injection into the patient's body.
  • Each housing preferably contains a power source having a capacity of at least 1 microwatt-hour, preferably a rechargeable battery, and power consuming circuitry preferably including a data signal transmitter and receiver and sensor/stimulator circuitry for driving an input/output transducer.
  • a preferred SCU is also implemented as a device capable of being injected into one patient's body.
  • Wireless communication between the SCU and the other implanted devices can be implemented in various ways, e.g., via a modulated sound signal, AC magnetic field, RF signal, or electrical conduction.
  • the SCU is remotely programmable, e.g., via wireless means, to interact with the implanted devices according to a treatment regimen.
  • the SCU is preferably powered via an internal power source, e.g., a rechargeable battery.
  • the SCU and other implanted devices are implemented substantially identically, being comprised of a sealed housing configured to be injected into the patient's body.
  • Each housing contains sensor/stimulator circuitry for driving an input/output transducer, e.g., an electrode, to enable it to additionally operate as a sensor and/or stimulator.
  • the SCU could be implemented as an implantable but non-injectable housing which would permit it to be physically larger enabling it to accommodate larger, higher capacity components, e.g., battery, microcontroller, etc.
  • the SCU could be implemented in a housing configured for carrying on the patient's body outside of the skin defined envelope, e.g., in a wrist band.
  • the commands transmitted by the SCU can be used to remotely configure the operation of the other implanted devices and/or to interrogate the status of those devices.
  • various operating parameters e.g., the pulse frequency, pulse width, trigger delays, etc.
  • the sensitivity of the sensor circuitry and/or the interrogation of a sensed parameter e.g., battery status, can be remotely specified by the SCU.
  • the SCU and/or each implantable device includes a programmable memory for storing a set of default parameters. In the event of power loss, SCU failure, or any other catastrophic occurrence, all devices default to the safe harbor default parameters.
  • the default parameters can be programmed differently depending upon the condition being treated.
  • the system includes a switch preferably actuatable by an external DC magnetic field, for resetting the system to its default parameters.
  • a patient with nerve damage can have a damaged nerve “replaced” by an implanted SCU and one or more implanted sensors and stimulators, each of which contains its own internal power source.
  • the SCU would monitor a first implanted sensor for a signal originating from the patient's brain and responsively transmit command signals to one or more stimulators implanted past the point of nerve damage.
  • the SCU could monitor additional sensors to determine variations in body parameters and, in a closed loop manner, react to control the command signals to achieve the desired treatment regimen.
  • FIG. 1 is a simplified block diagram of the system of the present invention comprised of implanted devices, e.g., microstimulators, microsensors and microtransponders, under control of an implanted system control unit (SCU);
  • implanted devices e.g., microstimulators, microsensors and microtransponders
  • SCU system control unit
  • FIG. 2 comprises a block diagram of the system of FIG. 1 showing the functional elements that form the system control unit and implanted microstimulators, microsensors and microtransponders;
  • FIG. 3A comprises a block diagram of an exemplary implanted device, as shown in the parent application, including a battery for powering the device for a period of time in excess of one hour in response to a command from the system control unit;
  • FIG. 3B comprises a simplified block diagram of controller circuitry that can be substituted for the controller circuitry of FIG. 3A, thus permitting a single device to be configured as a system control unit and/or a microstimulator and/or a microsensor and/or a microtransponder;
  • FIG. 4 is a simplified diagram showing the basic format of data messages for commanding/interrogating the implanted microstimulators, microsensors and microtransponders which form a portion of the present invention
  • FIG. 5 shows an exemplary flow chart of the use of the present system in an open loop mode for controlling/monitoring a plurality of implanted devices, e.g., microstimulators, microsensors;
  • FIG. 6 shows a flow chart of the optional use of a translation table for communicating with microstimulators and/or microsensors via microtransponders;
  • FIG. 7 shows a simplified flow chart of the use of closed loop control of a microstimulator by altering commands from the system control unit in response to status data received from a microsensor;
  • FIG. 8 shows an exemplary injury, i.e., a damaged nerve, and the placement of a plurality of implanted devices, i.e., microstimulators, microsensors and a microtransponder under control of the system control unit for “replacing” the damaged nerve;
  • a plurality of implanted devices i.e., microstimulators, microsensors and a microtransponder under control of the system control unit for “replacing” the damaged nerve
  • FIG. 9 shows a simplified flow chart of the control of the implanted devices of FIG. 8 by the system control unit
  • FIGS. 10 A and 10 BD show two side cutaway views of the presently preferred embodiment of an implantable ceramic tube suitable for the housing the system control unit and/or microstimulators and/or microsensors and/or microtransponders;
  • FIG. 11 illustrates an exemplary battery suitable for powering the implantable devices which comprise the components of the present invention.
  • FIG. 12 shows an exemplary housing suitable for an implantable SCU having a battery enclosed within that has a capacity of at least 1 watt-hour.
  • the present invention is directed to a system for monitoring and/or affecting parameters of a patient's body and more particularly to such a system comprised of a system control unit (SCU) and one or more devices implanted in a patient's body, i.e., within the envelope defined by the patient's skin.
  • SCU system control unit
  • Each such implantable device is configured to be monitored and/or controlled by the SCU via a wireless communication channel.
  • the SCU comprises a programmable unit capable of (1) transmitting commands to at least some of a plurality of implanted devices and (2) receiving data signals from at least some of those implanted devices.
  • the system operates in closed loop fashion whereby the commands transmitted by the SCU are dependent, in part, on the content of the data signals received by the SCU.
  • each implanted device is configured similarly to the devices described in Applicants' parent application Ser. No. ______ and typically comprises a sealed housing suitable for injection into the patient's body.
  • Each housing preferably contains a power source having a capacity of at least 1 microwatt-hour, preferably a rechargeable battery, and power consuming circuitry preferably including a data signal transmitter and receiver and sensor/stimulator circuitry for driving an input/output transducer.
  • FIG. 1 (essentially corresponding to FIG. 2 of the parent application) and FIG. 2 show an exemplary system 300 made of implanted devices 100 , preferably battery powered, under control of a system control unit (SCU) 302 , preferably also implanted beneath a patient's skin 12 .
  • SCU system control unit
  • potential implanted devices 100 include stimulators , e.g., 100 a , sensors e.g., 100 c , and transponders, e.g., 100 d.
  • the stimulators e.g., 100 a
  • the sensors e.g., 100 c
  • the sensors can be remotely programmed to sense one or more physiological or biological parameters in the implanted environment of the device, e.g., temperature, glucose level, O 2 content, etc.
  • Transponders e.g., 100 d
  • these stimulators, sensors and transponders are contained in sealed elongate housing having an axial dimension of less than 60 mm and lateral dimension of less than 6 mm. Accordingly, such stimulators, sensors and transponders are respectively referred to as microstimulators, microsensors, and microtransponders. Such microstimulators and microsensors can thus be positioned beneath the skin within a patient's body using a hypodermic type insertion tool 176 .
  • microstimulators and microsensors are remotely programmed and interrogated via a wireless communication channel, e.g., modulated AC magnetic, sound (i.e., ultrasonic), RF or electric fields, typically originating from control devices external to the patient's body, e.g., a clinicians's programmer 172 or patient control unit 174 .
  • the clinician's programmer 172 is used to program a single continuous or one time pulse sequence into each microstimulator and/or measure a biological parameter from one or more microsensors.
  • the patient control unit 174 typically communicates with the implanted devices 100 , e.g., microsensors 100 c , to monitor biological parameters.
  • each implanted device is manufactured with an identification code (ID) 303 specified in address storage circuitry 108 (see FIG. 3A) as described in the parent application.
  • ID identification code
  • the capabilities of such implanted devices can be further expanded.
  • the SCU 302 in an open loop mode (described below in reference to FIG. 5), the SCU 302 can be programmed to periodically initiate tasks, e.g., perform real time tasking, such as transmitting commands to microstimulators according to a prescribed treatment regimen or periodically monitor biological parameters to determine a patient's status or the effectiveness of a treatment regimen.
  • the SCU 302 in a closed loop mode (described below in reference to FIGS. 7 - 9 ), the SCU 302 periodically interrogates one or more microsensors and accordingly adjust the commands transmitted to one or more microstimulators.
  • FIG. 2 shows the system 300 of the present invention comprised of (1) one or more implantable devices 100 operable to sense and/or stimulate a patient's body parameter in accordance with one or more controllable operating parameters and (2) the SCU, 302 .
  • the SCU 302 is primarily comprised of (1) a housing 206 , preferably sealed and configured for implantation beneath the skin of the patient's body as described in the parent application in reference to the implanted devices 100 , (2) a signal transmitter 304 in the housing 206 for transmitting command signals, (3) a signal receiver 306 in the housing 206 for receiving status signals, and (4) a programmable controller 308 , e.g., a microcontroller or state machine, in the housing 206 responsive to received status signals for producing command signals for transmission by the signal transmitter 304 to other implantable devices 100 .
  • a programmable controller 308 e.g., a microcontroller or state machine
  • the sequence of operations of the programmable controller 308 is determined by an instruction list, i.e., a program, stored in program storage 310 , coupled to the programmable controller 308 .
  • the program storage 310 can be a nonvolatile memory device, e.g., ROM, manufactured with a program corresponding to a prescribed treatment regimen, it is preferably that at least a portion of the program storage 310 be an alterable form of memory, e.g., RAM, EEPROM, etc., whose contents can be remotely altered as described further below. However, it is additionally preferable that a portion of the program storage 310 be nonvolatile so that a default program is always present.
  • the rate at which the program contained within the program storage 310 is executed is determined by clock 312 , preferably a real time clock that permits tasks to be scheduled at specified times of day.
  • the signal transmitter 304 and signal receiver 306 preferably communicate with implanted devices 100 using sound means, i.e., mechanical vibrations, using a transducer having a carrier frequency modulated by a command data signal.
  • sound means i.e., mechanical vibrations
  • a carrier frequency of 100 KHz is used which corresponds to a frequency that freely passes through a typical body's fluids and tissues.
  • sound means that operate at any frequency, e.g., greater than 1 Hz, are also considered to be within the scope of the present invention.
  • the signal transmitter 304 and signal receiver 306 can communicate using modulated AC magnetic, RF, or electric fields.
  • the clinician's programmer 172 and/or the patient control unit 174 and/or other external control devices can also communicate with the implanted devices 100 , as described in the parent application, preferably using a modulated AC magnetic field.
  • such external devices can communicate with the SCU 302 via a transceiver 314 coupled to the programmable controller 308 . Since, in a preferred operating mode, the signal transmitter 304 and signal receiver 306 operate using sound means, a separate transceiver 314 which operates using magnetic means is used far communication with external devices. However, a single transmitter 304 /receiver 306 can be used in place of transceiver 314 if a common communication means is used.
  • FIG. 3A comprises a block diagram of an exemplary implanted device 100 (as shown in FIG. 2 of the parent application) which includes a battery 104 , preferably rechargeable, for powering the device for a period of time in excess of one hour and responsive to command signals from a remote device, e.g., the SCU 302 .
  • the implantable device 100 is preferably configurable to alternatively operate as a microstimulator and/or microsensor and/or microtransponder due to the commonality of most of the circuitry contained within.
  • Such circuitry can be further expanded to permit a common block of circuitry to also perform the functions required for the SCU 302 . Accordingly, FIG.
  • FIG. 3B shows an alternative implementation of the controller circuitry 106 of FIG. 3A that is suitable for implementing a microstimulator and/or a microsensor and/or a microtransponder and/or the SCU 302 .
  • the configuration data storage 132 can be alternatively used as the program storage 310 when the implantable device 100 is used as the SCU 302 .
  • XMTR 168 corresponds to the signal transmitter 304 and the RCVR 114 b corresponds to the signal receiver 306 (preferably operable using sound means via transducer 138 ) and the RCVR 114 a and XMTR 146 correspond to the transceiver 314 (preferably operable using magnetic means via coil 116 ).
  • the contents of the program storage 310 i.e., the software that controls the operation of the programmable controller 308
  • the contents of the program storage 310 can be remotely downloaded, e.g., from the clinician's programmer 172 using data modulated onto an AC magnetic field.
  • the contents of the program storage 310 for each SCU 302 be protected from an inadvertent change.
  • the contents of the address storage circuitry 108 i.e., the ID 303
  • the SCU 302 be operable for an extended period of time, e.g., in excess of one hour, from an internal power supply 316 .
  • a primary battery i.e., a nonrechargeable battery
  • the power supply 316 include a rechargeable battery, e.g., battery 104 as described in the parent application, that can be recharged via an AC magnetic field produced external to the patient's body.
  • the power supply 102 of FIG. 3A (described in detail in the parent application) is the preferred power supply 316 for the SCU 302 as well.
  • the battery-powered devices 100 of the parent invention are preferably configurable to operate in a plurality of operation modes, e.g., via a communicated command signal.
  • device 100 is remotely configured to be a microstimulator, e.g., 100 a and 100 b.
  • controller 130 commands stimulation circuitry 110 to generate a sequence of drive pulses through electrodes 112 to stimulate tissue, e.g., a nerve, proximate to the implanted location of the microstimulator, e.g., 100 a or 100 b.
  • a programmable pulse generator 178 and voltage multiplier 180 are configured with parameters (see Table I) corresponding to a desired pulse sequence and specifying now much to multiply the battery voltage (e.g., by summing charged capacitors or similarly charged battery portions) to generate a desired compliance voltage V c .
  • a first FET 182 is periodically energized to store charge into capacitor 183 (in a first direction at a low current flow rate through the body tissue) and a second FET 184 is periodically energized to discharge capacitor 183 in an opposing direction at a higher current flow rate which stimulates a nearby nerve.
  • electrodes can be selected that will form an equivalent capacitor within the body tissue.
  • the battery-powered implantable device 100 can be configured to operate as a microsensor, e.g., 100 c , that can sense one or more physiological or biological parameters in the implanted environment of the device.
  • the system control unit 302 periodically requests the sensed data from each microsensor 100 c using its ID stored in address storage 108 , and responsively sends command signals to microstimulators, e.g., 100 a and 100 b, adjusted accordingly to the sensed data.
  • sensor circuitry 188 can coupled to the electrodes 112 to sense or otherwise used to measure a biological parameter, e.g., temperature, glucose level, or O 2 content and provided the sensed data to the controller circuitry 106 .
  • the sensor circuitry includes a programmable bandpass filter and an analog to digital (A/D) converter that can sense and accordingly convert the voltage levels across the electrodes 112 into a digital quantity.
  • the sensor circuitry can include one or more sense amplifiers to determine if the measured voltage exceeds a threshold voltage value or is within a specified voltage range.
  • the sensor circuitry 188 can be configurable to include integration circuitry to further process the sensed voltage.
  • the operation modes of the sensor circuitry 188 is remotely programable via the devices communication interface as shown below in Table II.
  • TABLE II Sensing Parameters Input voltage range: 5 ⁇ v to 1 V Bandpass filter rolloff: 24 dB Low frequency cutoff choices: 3, 10, 30, 100, 300, 1000 Hz High frequency cutoff choices: 3, 10, 30, 100, 300, 1000 Hz Integrator frequency choices: 1 PPS to 100 PPS Amplitude threshold 4 bits of resolution for detection choices:
  • the sensing capabilities of a microsensor include the capability to monitor the battery status via path 124 from the charging circuit 122 and can additionally include using the ultrasonic transducer 138 or the coil 116 to respectively measure the magnetic or ultrasonic signal magnitudes (or transit durations) of signals transmitted between a pair of implanted devices and thus determine the relative locations of these devices. This information can be used to determine the amount of body movement, e.g., the amount that an elbow or finger is bent, and thus form a portion of a closed loop motion control system.
  • the battery-powered implantable device 100 can be configured to operate as a microtransponder, e.g., 100 d.
  • the microtransponder receives (via the aforementioned receiver means, e.g., AC magnetic, sonic, RF or electric) a first command signal from the SCU 302 and retransmits this signal (preferably after reformatting) to other implanted devices (e.g., microstimulators, microsensors, and/or microtransponders) using the aforementioned transmitter means (e.g., magnetic, sonic, RF or electric).
  • the aforementioned receiver means e.g., AC magnetic, sonic, RF or electric
  • a microtransponder may receive one mode of command signal, e.g., it may retransmit the signal in another mode, e.g., ultrasonic.
  • clinician's programmer 172 may emit a modulated magnetic signal using a magnetic emitter 190 to program/command the implanted devices 100 .
  • the magnitude of the emitted signal may not be sufficient to be successfully received by all of the implanted devices 100 .
  • a microtransponder 100 d may receive the modulated magnetic signal and retransmit it (preferably after reformatting) as a modulated ultrasonic signal which can pass through the body with fewer restrictions.
  • the patient control unit 174 may need to monitor a microsensor 100 c in a patient's foot. Despite the efficiency of ultrasonic communication in a patient's body, an ultrasonic signal could still be insufficient to pass from a patient's foot to a patient's wrist (the typical location of the patient control unit 174 ). As such, a microtransponder 100 d could be implanted in the patient's torso to improve the communication link.
  • FIG. 4 shows the basic format of an exemplary message 192 for communicating with the aforementioned battery-powered devices 100 , all of which are preconfigured with an address (ID), preferably unique to that device, in their identification storage 108 to operate in one or more of the following modes (1) for nerve stimulation, i.e., as a microstimulator, (2) for biological parameter monitoring, i.e., as a microsensor, and/or (3) for retransmitting received signals after reformatting to other implanted devices, i.e., as a microtransponder.
  • ID address
  • the command message 192 is primarily comprised of a (1) start portion 194 (one or more bits to signify the start of the message and to synchronize the bit timing between transmitters and receivers, (2) a mode portion 196 (designating the operating mode, e.g., microstimulator, microsensor, microtransponder, or group mode), (3) an address (ID) portion 198 (corresponding to either the identification address 108 or a programmed group ID), (4) a data field portion 200 (containing command data for the prescribed operation), (5) an error checking portion 202 (for ensuring the validity of the message 192 , e.g., by use of a parity bit), and (6) a stop portion 204 (for designating the end of the message 192 ).
  • start portion 194 one or more bits to signify the start of the message and to synchronize the bit timing between transmitters and receivers
  • a mode portion 196 designating the operating mode, e.g., microstimulator, microsensor, microtransponder, or group mode
  • each device can be separately configured, controlled and/or sensed as part of a system or controlling one or more neural pathways within a patient's body.
  • each device 100 can be programmed with a group ID (e.g., a 4 bit value) which is stored in its configuration data storage 132 .
  • a device 100 e.g., a microstimulator
  • receives a group ID message that matches its stored group ID it responds as if the message was directed to its identification address 108 .
  • a plurality of microstimulators e.g., 100 a and 100 b, can be commanded with a single message. This mode is of particular use when precise timing is desired among the stimulation of a group of nerves.
  • Group Write Command Set the microstimulators/microsensors within the group specified in the address field 198 to the designated parameter value.
  • Stimulate Command Enable a sequence of drive pulses from the microstimulator specified in the address field 198 according to previously programmed and/or default values.
  • Group Stimulate Command Enable a sequence of drive pulses from the microstimulators within the group specified in the address field 198 according to previously programmed and/or default values.
  • Unit Off Command Disable the output of the microstimulator specified in the address field 198 .
  • Group Stimulate Command Disable the output of the microstimulators within the group specified in the address field 198 .
  • Read Command Cause the microsensor designated in the address field 198 to read the previously programmed and/or default sensor value according to previously programmed and/or default values.
  • Read Battery Status Command Cause the microsensor designated in the address field 198 to return its battery status.
  • Group Command Use the microstimulator/microsensor designated in the address field 198 to be assigned to the group defined in the microstimulator data field 200 .
  • Set Telemetry Mode Command Configure the microtransponder designated in the address field 198 as to its input mode (e.g., AC magnetic, sonic, etc.), output mode (e.g., AC magnetic, sonic, etc.), message length, etc.
  • input mode e.g., AC magnetic, sonic, etc.
  • output mode e.g., AC magnetic, sonic, etc.
  • message length etc.
  • Status Reply Command Return the requested status/sensor data to the requesting unit, e.g., the SCU.
  • Download Program Command Download program/safe harbor routines to the device, e.g., SCU, microstimulator, etc., specified in the address field 198 .
  • FIG. 5 shows a block diagram of an exemplary open loop control program, i.e., a task scheduler 320 , for controlling/monitoring a body function/parameter.
  • the programmable controller 308 is responsive to the clock 312 (preferably crystal controlled to thus permit real time scheduling) in determining when to perform any of a plurality of tasks.
  • the programmable controller 308 first determines in block 322 if is now at a time designated as T EVENT1 (or at least within a sampling error of that time), e.g., at 1:00 AM. If so, the programmable controller 308 transmits a designated command to microstimulator A (ST A ) in block 324 .
  • control program continues where commands are sent to a plurality of stimulators and concludes in block 326 where a designated command is sent to microstimulator X (ST X ).
  • a subprocess e.g., a subroutine
  • the task scheduler 320 continues through multiple time event detection blocks until in block 328 it determines whether the time T EVENTM has arrived. If so, the process continues at block 330 where, in this case, a single command is sent to microstimulator M (ST M ).
  • the task scheduler 320 determines when it is the scheduled time, i.e., T EVENT0 , to execute a status request from microsensor A (SE A ). Is so, a subprocess, e.g., a subroutine, commences at block 334 where a command is sent to microsensor A (SE A ) to request sensor data and/or specify sensing criteria. Microsensor A (SE A ) does not instantaneously respond. Accordingly, the programmable controller 308 waits for a response in block 336 .
  • a subprocess e.g., a subroutine
  • the returned sensor status data from microsensor A (SE A ) is stored in a portion of the memory, e.g., a volatile portion of the program storage 310 , of the programmable controller 308 .
  • the task scheduler 320 can be a programmed sequence, i.e., defined in software stored in the program storage 310 , or, alternatively, a predefined function controlled by a table of parameters similarly stored in the program storage 310 .
  • a similar process can be used where the SCU 302 periodically interrogates each implantable device 100 to determine its battery status.
  • FIG. 6 shows an exemplary use of an optional translation table 340 for communicating between the SCU 302 and microstimulators, e.g., 100 a , and/or microsensors, e.g., 100 c , via microtransponders, e.g., 100 d.
  • a microtransponder, e.g., 100 d is used when the communication range of the SCU 302 is insufficient to reliably communicate with other implanted devices 100 .
  • the SCU 302 instead directs a data message, i.e., a data packet, to an intermediary microtransponder, e.g., 100 d, which retransmits the data packet to a destination device 100 .
  • the translation table 340 contains pairs of corresponding entries, i.e., first entries 342 corresponding to destination addresses and second entries 344 corresponding to the intermediary microtransponder addresses.
  • the SCU 302 determines, e.g., according to a timed event designated in the program storage 310 , that a command is to be sent to a designated destination device (see block 346 )
  • the SCU 302 searches the first entries 342 of the translation table 340 , for the destination device address, e.g., ST M .
  • the SCU 302 fetches the corresponding second table entry 344 in block 348 and transmits the command to that address.
  • the SCU 302 transmits commands directly to the implanted device 100 .
  • the second table entry 344 e.g., T N
  • the SCU 302 transmits commands via an intermediary microtransponder, e.g., 100 d.
  • the use of the translation table 340 is optional since the intermediary addresses can, instead, be programmed directly into a control program contained in the program storage 310 .
  • the translation table 340 is preferably contained in programmable memory, e.g., RAM or EPROM, and can be a portion of the program storage 310 . While the translation table 340 can be remotely programmed, e.g., via a modulated signal from the clinician's programmer 172 , it is also envisioned that the SCU 302 can reprogram the translation table 340 if the communications degrade.
  • programmable memory e.g., RAM or EPROM
  • FIG. 7 is an exemplary block diagram showing the use of the system of the present invention to perform closed loop control of a body function.
  • the SCU 302 requests status from microsensor A (SE A ).
  • SE A microsensor A
  • the SCU 302 in block 354 , then determines whether a current command given to a microstimulator is satisfactory and, if necessary, determines a new command and transmits the new command to the microstimulator A in block 356 .
  • microsensor A SE A
  • the SCU 302 could transmit a command to microstimulator A (ST A ) to adjust the sequence of drive pulses, e.g., in magnitude, duty cycle, etc., and accordingly change the voltage sensed by microsensor A (SE A ).
  • closed loop i.e., feedback
  • the characteristics of the feedback (position, integral, derivative (PID)) control are preferably program controlled by the SCU 302 according to the control program contained in program storage 310 .
  • FIG. 8 shows an exemplary injury treatable by embodiments of the present system 300 .
  • the neural pathway has been damaged, e.g, severed, just above the a patient's left elbow.
  • the goal of this exemplary system is to bypass the damaged neural pathway to permit the patient to regain control of the left hand.
  • An SCU 302 is implanted within the patient's torso to control plurality of stimulators, ST 1 -ST 3 , implanted proximate to the muscles respectively controlling the patient's thumb and fingers.
  • microsensor 1 SE 1
  • SE 1 is implanted proximate to an undamaged nerve portion where it can sense a signal generated from the patient's brain when the patient wants hand closure.
  • Optional microsensor 2 (SE 2 ) is implanted in a portion of the patient's hand where it can sense a signal corresponding to stimulation/motion of the patient's pinky finger and microsensor 3 (SE 3 ) is implanted and configured to measure a signal corresponding to grip pressure generated when the fingers of the patient's hand are closed.
  • an optional microtransponder (T 1 ) is shown which can be used to improve the communication between the SCU 302 and the implanted devices.
  • FIG. 9 shows an exemplary flow chart for the operation of the SCU 302 in association with the implanted devices in the exemplary system of FIG. 8.
  • the SCU 302 interrogates microsensor 1 (SE 1 ) to determine if the patient is requesting actuation of his fingers. If not, a command is transmitted in block 362 to all of the stimulators (ST 1 -ST 3 ) to open the patient's hand, i.e., to de-energize the muscles which close the patient's fingers.
  • microsensor 1 senses a signal to actuate the patient's fingers
  • the SCU 302 determines in block 364 whether the stimulators ST 1 -ST 3 are currently energized, i.e., generating a sequence of drive pulses. If not, the SCU 302 executes instructions to energize the simulators.
  • each of the stimulators are simultaneously (subject to formatting and transmission delays) commanded to energize in block 366 a. However, the command signal given to each one specifies a different start delay time (using the BON parameter). Accordingly, there is a stagger between the actuation/closing of each finger.
  • a second optional path 368 the microstimulators are consecutively energized by a delay ⁇ .
  • microstimulator 1 ST 1
  • a delay is executed within the SCU 302 in block 368 b
  • paths 366 and 368 perform essentially the same function.
  • the interdevice timing is performed by the clocks within each implanted device 100 while in math 368 , the SCU 302 is responsible for providing the interdevice timing.
  • the SCU 302 actuates a first microstimulator (ST 1 ) in block 370 a and waits in block 370 b for its corresponding muscle to be actuated, as determined by microsensor 2 (SE 2 ), before actuating the remaining stimulators (ST 2 -ST 3 ) in block 370 c.
  • This implementation could provide more coordinated movement in some situations.
  • closed loop grip pressure control is performed in blocks 372 a and 372 b by periodically reading the status of microsensor 3 (SE 3 ) and adjusting the commands given to the stimulators (ST 1 -ST 3 ) accordingly. Consequently, this exemplary system has enabled the patient to regain control of his hand including coordinated motion and grip pressure control of the patient's fingers.
  • a magnetic sensor 186 is shown.
  • a sensor 186 could be used to disable the operation of an implanted device 100 , e.g., to stop the operation of such devices in an emergency situation, in response to a DC magnetic field, preferably from an externally positioned safety magnet 187 .
  • a further implementation is disclosed herein.
  • the magnetic sensor 186 can be implemented using various devices. Exemplary of such devices are devices manufactured by Nonvolatile Electronics, Inc. (e.g., their AA, AB, AC, AD, or AG series), Hall effect sensors, and subminiature reed switches.
  • Such miniature devices are configurable to be placed within the housing of the disclosed SCU 302 and implantable devices 100 . While essentially passive magnetic sensors, e.g., reed switches, are possible, the remaining devices include active circuitry that consumes power during detection of the DC magnetic field. Accordingly, it is preferred that controller circuitry 302 periodically, e.g., once a second, provide power the magnetic sensor 186 and sample the sensor's output signal 374 during that sampling period.
  • the programmable controller 308 is a microcontroller operating under software control wherein the software is located within the program storage 310 .
  • the SCU 302 preferably includes an input 376 , e.g., a non maskable interrupt (NMI), which causes a safe harbor subroutine 378 , preferably located within the program storage 310 , to be executed.
  • NMI non maskable interrupt
  • failure or potential failure modes e.g., low voltage or over temperature conditions, can be used to cause the safe harbor subroutine 378 to be executed.
  • such a subroutine could cause a sequence of commands to be transmitted to set each microstimulator into a safe condition for the particular patient configuration, typically disabling each microstimulator.
  • the safe harbor condition could be to set certain stimulators to generate a prescribed sequence of drive pulses.
  • the safe harbor subroutine 378 can be downloaded from an external device, e.g., the clinician's programmer 172 , into the program storage 310 , a nonvolatile storage device.
  • an external device e.g., the clinician's programmer 172
  • a default safe harbor subroutine be used instead.
  • This default subroutine preferably stored in nonvolatile storage that is not user programmable, e.g., ROM, that is otherwise a portion of the program storage 310 .
  • This default subroutine is preferably general purpose and typically is limited to commands that turn off all potential stimulators.
  • programmable safe harbor subroutines 378 can exist in the implanted stimulators 100 . Accordingly, a safe harbor subroutine could be individually programmed into each microstimulator that is customized for the environments of that microstimulator and a safe harbor subroutine for the SCU 302 could then be designated that disables the SCU 302 , i.e. causes the SCU 302 to not issue subsequent commands to other implanted devices 100 .
  • FIGS. 10 A and 10 BD show two side cutaway views of the presently preferred construction of the sealed housing 206 , the battery 104 and the circuitry (implemented on one or more IC chips 216 to implement electronic portions or the SCU 302 ) contained within.
  • the housing 206 is comprised of an insulating ceramic tube 260 brazed onto a first end cap forming electrode 112 a via a braze 262 .
  • a metal ring 264 At the other end of the ceramic tube 260 is a metal ring 264 that is also brazed onto the ceramic tube 260 .
  • the circuitry within, i.e., a capacitor 183 (used when in a microstimulator mode), battery 104 , IC chips 216 , and a spring 266 is attached to an opposing second end cap forming electrode 112 b.
  • a drop of conductive epoxy is used to glue the capacitor 183 to the end cap 112 a and is held in position by spring 266 as the glue takes hold.
  • the IC chips 216 are mounted on a circuit board 268 over which half circular longitudinal ferrite slates 270 are attached.
  • the coil 116 is wrapped around the ferrite plates 270 and attached to IC chips 216 .
  • a getter 272 mounted surrounding the spring 266 , is preferably used to increase the hermeticity of the SCU 302 by absorbing water introduced therein.
  • An exemplary getter 272 absorbs 70 times its volume in water. While holding the circuitry and the end cap 112 b together, one can laser weld the end cap 112 b to the ring 264 .
  • a platinum, iridium, or platinum-iridium disk or plate 274 is preferably welded to the end caps of the SCU 302 to minimize the impedance of the connection to the body tissue.
  • an exemplary battery 104 is described more fully below in connection with the description of FIG. 11.
  • the battery 104 is made from appropriate materials so as to provide a power capacity of at least 1 microwatt-hour, preferably constructed from a battery having an energy density of about 240 mW-Hr/cm 3 .
  • a Li—I battery advantageously provides such an energy density.
  • an Li—I—Sn battery provides an energy density up to 360 mW-Hr/cm 3 . Any of these batteries, or other batteries providing a power capacity of at least 1 microwatt-hour may be used with implanted devices of the present invention.
  • the battery voltage V of an exemplary battery is nominally 3.6 volts, which is more than adequate for operating the CMOS circuits preferably used to implement the IC chip(s) 216 , and/or other electronic circuitry, within the SCU 302 .
  • the battery voltage V in general, is preferably not allowed to discharge below about 2.55 volts, or permanent damage may result.
  • the battery 104 should preferably not be charged to a level above about 4.2 volts, or else permanent damage may result.
  • a charging circuit 122 (discussed in the parent application) is used to avoid any potentially damaging discharge or overcharge.
  • the battery 104 may take many forms, any of which may be used so long as the battery can be made to fit within the small volume available.
  • the battery 104 may be either a primary battery or a rechargeable battery.
  • a primary battery offers the advantage of a longer life for a given energy output but presents the disadvantage of not being rechargeable (which means once its energy has been used up, the implanted device no longer functions).
  • the SCU 302 and/or devices 100 need only be used for a short time (after which they can be explanted and discarded, or simply left implanted as benign medical devices).
  • a rechargeable battery is clearly the preferred type of energy choice, as the tissue stimulation provided by the microstimulator is of a recurring nature.
  • a typical SCU 302 made in accordance with the present invention is no larger than about 60 mm long and 8 mm in diameter, preferably no larger than 60 mm long and 6 mm in diameter, and includes even smaller embodiments, e.g., 15 mm long with an O.D. of 2.2 mm (resulting in an I.D. of about 2 mm).
  • FIG. 11 shows an exemplary battery 104 typical of those disclosed in the parent application.
  • each cylindrical electrode includes a gap or slit 242 ; with the cylindrical electrodes 222 and 224 on each side of the gap 242 forming a common connection point for tabs 244 and 246 which serve as the electrical terminals for the battery.
  • the electrodes 222 and 224 are separated by a suitable separator 248 .
  • the gap 242 minimizes the flow of eddy currents in the electrodes.
  • concentric cylindrical electrodes 222 there are four concentric cylindrical electrodes 222 , the outer one (largest diameter) of which may function as the battery case 234 , and three concentric electrodes 224 interleaved between the electrodes 222 , with six concentric cylindrical separator layers 248 separating each electrode 222 or 224 from the adjacent electrodes.
  • a preferred embodiment of the present invention is comprised of an implanted SCU 302 and a plurality of implanted devices 100 , each of which contains its own rechargeable battery 104 .
  • a patient is essentially independent of any external apparatus between battery chargings (which generally occur no more often than once an hour).
  • it may be adequate to use a power supply analogous to that described in U.S. Pat. No. 5,324,316 that only provides power while an external AC magnetic field is being provided, e.g., from charger 118 .
  • the SCU 302 may be implemented as an external device, e.g., within a watch-shaped housing that can be attached to a patient's wrist in a similar manner to the patient control unit 174 .
  • the power consumption of the SCU 302 is primarily dependent upon the circuitry implementation, preferably CMOS, the circuitry complexity and the clock speed.
  • CMOS complementary metal-oxide-semiconductor
  • a CMOS implemented state machine will be sufficient to provide the required capabilities of the programmable controller 308 .
  • a microcontroller may be required. As the complexity of such microcontrollers increases (along with its transistor count), so does its power consumption. Accordingly, a larger battery having a capacity of 1 watt-hour is preferred. While a primary battery is possible, it is preferable that a rechargeable battery be used.
  • FIG. 12 shows an exemplary implantable housing 380 suitable for such a device.

Abstract

A system for monitoring and/or affecting parameters of a patient's body and more particularly to such a system comprised of a system control unit (SCU) and one or more other devices, preferably battery-powered, implanted in the patient's body, i.e., within the envelope defined by the patient's skin. Each such implanted device is configured to be monitored and/or controlled by the SCU via a wireless communication channel. In accordance with the invention, the SCU comprises a programmable unit capable of (1) transmitting commands to at least some of a plurality of implanted devices and (2) receiving data signal from at least some of those implanted devices. In accordance with a preferred embodiment, the system operates in closed loop fashion whereby the commands transmitted by the SCU are dependent, in part, on the content of the data signals received by the SCU. In accordance with the invention, a preferred SCU is similarly implemented as a device capable of being implanted beneath a patient's skin, preferably having an axial dimension of less than 60 mm and a lateral dimension of less than 6 mm. Wireless communication between the SCU and the implanted devices is preferably implemented via a modulated sound signal, AC magnetic field, RF signal, or electric conduction.

Description

  • This application claims the benefit of U.S. Provisional Application No. 60/042,447 filed Mar. 27, 1997 and U.S. patent application Ser. No. ______, filed Feb. 25, 1998 entitled “Battery-Powered Patient Implantable Device” which in turn claims the benefit of U.S. Provisional Application No. 60/039,164 filed Feb. 26, 1997.[0001]
  • BACKGROUND OF THE INVENTION
  • The present invention relates to systems for monitoring and/or affecting parameters of a patient's body for the purpose of medical diagnosis and/or treatment. More particularly, systems in accordance with the invention are characterized by a plurality of devices, preferably battery-powered, configured for implanting within a patient's body, each device being configured to sense a body parameter, e.g., temperature, O[0002] 2 content, physical position, etc., and/or to affect a parameter, e.g., via nerve stimulation.
  • Applicants' parent application Ser. No. ______, entitled “Battery Powered Patient Implantable Device”, incorporated herein by reference, describes devices configured for implantation within a patient's body, i.e., beneath a patient's skin, for performing various functions including: (1) stimulation of body tissue, (2) sensing of body parameters, and (3) communicating between implanted devices and devices external to a patient's body. [0003]
  • SUMMARY OF THE INVENTION
  • The present invention is directed to a system for monitoring and/or affecting parameters of a patient's body and more particularly to such a system comprised of a system control unit (SCU) and one or more devices implanted in the patient's body, i.e., within the envelope defined by the patient's skin. Each said implanted device is configured to be monitored and/or controlled by the SCU via a wireless communication channel. [0004]
  • In accordance with the invention, the SCU comprises a programmable unit capable of (1) transmitting commands to at least some of a plurality of implanted devices and (2) receiving data signals from at least some of those implanted devices. In accordance with a preferred embodiment, the system operates in closed loop fashion whereby the commands transmitted by the SCU are dependent, in part, on the content of the data signals received by the SCU. [0005]
  • In accordance with a preferred embodiment, each implanted device is configured similarly to the devices described in Applicants' parent application Ser. No. ______, and typically comprises a sealed housing suitable for injection into the patient's body. Each housing preferably contains a power source having a capacity of at least 1 microwatt-hour, preferably a rechargeable battery, and power consuming circuitry preferably including a data signal transmitter and receiver and sensor/stimulator circuitry for driving an input/output transducer. [0006]
  • In accordance with a significant aspect of the preferred embodiment, a preferred SCU is also implemented as a device capable of being injected into one patient's body. Wireless communication between the SCU and the other implanted devices can be implemented in various ways, e.g., via a modulated sound signal, AC magnetic field, RF signal, or electrical conduction. [0007]
  • In accordance with a further aspect of the invention, the SCU is remotely programmable, e.g., via wireless means, to interact with the implanted devices according to a treatment regimen. In accordance with a preferred embodiment, the SCU is preferably powered via an internal power source, e.g., a rechargeable battery. Accordingly, an SCU combined with one or more battery-powered implantable devices, such as those described in the parent application, form a self-sufficient system for treating a patient. [0008]
  • In accordance with a preferred embodiment, the SCU and other implanted devices are implemented substantially identically, being comprised of a sealed housing configured to be injected into the patient's body. Each housing contains sensor/stimulator circuitry for driving an input/output transducer, e.g., an electrode, to enable it to additionally operate as a sensor and/or stimulator. [0009]
  • Alternatively, the SCU could be implemented as an implantable but non-injectable housing which would permit it to be physically larger enabling it to accommodate larger, higher capacity components, e.g., battery, microcontroller, etc. As a further alternative, the SCU could be implemented in a housing configured for carrying on the patient's body outside of the skin defined envelope, e.g., in a wrist band. [0010]
  • In accordance with the invention, the commands transmitted by the SCU can be used to remotely configure the operation of the other implanted devices and/or to interrogate the status of those devices. For example, various operating parameters, e.g., the pulse frequency, pulse width, trigger delays, etc., of each implanted device can be controlled or specified in one or more commands addressably transmitted to the device. Similarly, the sensitivity of the sensor circuitry and/or the interrogation of a sensed parameter, e.g., battery status, can be remotely specified by the SCU. [0011]
  • In accordance with a significant feature of the preferred embodiment, the SCU and/or each implantable device includes a programmable memory for storing a set of default parameters. In the event of power loss, SCU failure, or any other catastrophic occurrence, all devices default to the safe harbor default parameters. The default parameters can be programmed differently depending upon the condition being treated. In accordance with a further feature, the system includes a switch preferably actuatable by an external DC magnetic field, for resetting the system to its default parameters. [0012]
  • In an exemplary use of a system in accordance with the present invention, a patient with nerve damage can have a damaged nerve “replaced” by an implanted SCU and one or more implanted sensors and stimulators, each of which contains its own internal power source. In this exemplary system, the SCU would monitor a first implanted sensor for a signal originating from the patient's brain and responsively transmit command signals to one or more stimulators implanted past the point of nerve damage. Furthermore, the SCU could monitor additional sensors to determine variations in body parameters and, in a closed loop manner, react to control the command signals to achieve the desired treatment regimen. [0013]
  • The novel features of the invention are set forth with particularity in the appended claims. The invention will be best understood from the following description when read in conjunction with the accompanying drawings. [0014]
  • BRIEF DESCRIPTION OF THE DRAWINGS
  • FIG. 1 is a simplified block diagram of the system of the present invention comprised of implanted devices, e.g., microstimulators, microsensors and microtransponders, under control of an implanted system control unit (SCU); [0015]
  • FIG. 2 comprises a block diagram of the system of FIG. 1 showing the functional elements that form the system control unit and implanted microstimulators, microsensors and microtransponders; [0016]
  • FIG. 3A comprises a block diagram of an exemplary implanted device, as shown in the parent application, including a battery for powering the device for a period of time in excess of one hour in response to a command from the system control unit; [0017]
  • FIG. 3B comprises a simplified block diagram of controller circuitry that can be substituted for the controller circuitry of FIG. 3A, thus permitting a single device to be configured as a system control unit and/or a microstimulator and/or a microsensor and/or a microtransponder; [0018]
  • FIG. 4 is a simplified diagram showing the basic format of data messages for commanding/interrogating the implanted microstimulators, microsensors and microtransponders which form a portion of the present invention; [0019]
  • FIG. 5 shows an exemplary flow chart of the use of the present system in an open loop mode for controlling/monitoring a plurality of implanted devices, e.g., microstimulators, microsensors; [0020]
  • FIG. 6 shows a flow chart of the optional use of a translation table for communicating with microstimulators and/or microsensors via microtransponders; [0021]
  • FIG. 7 shows a simplified flow chart of the use of closed loop control of a microstimulator by altering commands from the system control unit in response to status data received from a microsensor; [0022]
  • FIG. 8 shows an exemplary injury, i.e., a damaged nerve, and the placement of a plurality of implanted devices, i.e., microstimulators, microsensors and a microtransponder under control of the system control unit for “replacing” the damaged nerve; [0023]
  • FIG. 9 shows a simplified flow chart of the control of the implanted devices of FIG. 8 by the system control unit; [0024]
  • FIGS. [0025] 10A and 10BD show two side cutaway views of the presently preferred embodiment of an implantable ceramic tube suitable for the housing the system control unit and/or microstimulators and/or microsensors and/or microtransponders;
  • FIG. 11 illustrates an exemplary battery suitable for powering the implantable devices which comprise the components of the present invention; and [0026]
  • FIG. 12 shows an exemplary housing suitable for an implantable SCU having a battery enclosed within that has a capacity of at least 1 watt-hour. [0027]
  • DESCRIPTION OF THE PREFERRED EMBODIMENTS
  • The present invention is directed to a system for monitoring and/or affecting parameters of a patient's body and more particularly to such a system comprised of a system control unit (SCU) and one or more devices implanted in a patient's body, i.e., within the envelope defined by the patient's skin. Each such implantable device is configured to be monitored and/or controlled by the SCU via a wireless communication channel. [0028]
  • In accordance with the invention, the SCU comprises a programmable unit capable of (1) transmitting commands to at least some of a plurality of implanted devices and (2) receiving data signals from at least some of those implanted devices. In accordance with a preferred embodiment, the system operates in closed loop fashion whereby the commands transmitted by the SCU are dependent, in part, on the content of the data signals received by the SCU. [0029]
  • In accordance with a preferred embodiment, each implanted device is configured similarly to the devices described in Applicants' parent application Ser. No. ______ and typically comprises a sealed housing suitable for injection into the patient's body. Each housing preferably contains a power source having a capacity of at least 1 microwatt-hour, preferably a rechargeable battery, and power consuming circuitry preferably including a data signal transmitter and receiver and sensor/stimulator circuitry for driving an input/output transducer. [0030]
  • FIG. 1 (essentially corresponding to FIG. 2 of the parent application) and FIG. 2 show an [0031] exemplary system 300 made of implanted devices 100, preferably battery powered, under control of a system control unit (SCU) 302, preferably also implanted beneath a patient's skin 12. As described in the parent application, potential implanted devices 100 (see also the block diagram shown in FIG. 3A) include stimulators , e.g., 100 a, sensors e.g., 100 c, and transponders, e.g., 100 d. The stimulators, e.g., 100 a, can be remotely programmed to output a sequence of drive pulses to body tissue proximate to its implanted location via attached electrodes. The sensors, e.g., 100 c, can be remotely programmed to sense one or more physiological or biological parameters in the implanted environment of the device, e.g., temperature, glucose level, O2 content, etc. Transponders, e.g., 100 d, are devices which can be used to extend the interbody communication range between stimulators and sensors and other devices, e.g., a clinician's programmer 172 and the patient control unit 174. Preferably, these stimulators, sensors and transponders are contained in sealed elongate housing having an axial dimension of less than 60 mm and lateral dimension of less than 6 mm. Accordingly, such stimulators, sensors and transponders are respectively referred to as microstimulators, microsensors, and microtransponders. Such microstimulators and microsensors can thus be positioned beneath the skin within a patient's body using a hypodermic type insertion tool 176.
  • As described in the parent application, microstimulators and microsensors are remotely programmed and interrogated via a wireless communication channel, e.g., modulated AC magnetic, sound (i.e., ultrasonic), RF or electric fields, typically originating from control devices external to the patient's body, e.g., a clinicians's [0032] programmer 172 or patient control unit 174. Typically, the clinician's programmer 172 is used to program a single continuous or one time pulse sequence into each microstimulator and/or measure a biological parameter from one or more microsensors. Similarly, the patient control unit 174 typically communicates with the implanted devices 100, e.g., microsensors 100 c, to monitor biological parameters. In order to distinguish each implanted device over the communication channel, each implanted device is manufactured with an identification code (ID) 303 specified in address storage circuitry 108 (see FIG. 3A) as described in the parent application.
  • By using one or more such implantable devices in conjunction with the [0033] SCU 302 of the present invention, the capabilities of such implanted devices can be further expanded. For example, in an open loop mode (described below in reference to FIG. 5), the SCU 302 can be programmed to periodically initiate tasks, e.g., perform real time tasking, such as transmitting commands to microstimulators according to a prescribed treatment regimen or periodically monitor biological parameters to determine a patient's status or the effectiveness of a treatment regimen. Alternatively, in a closed loop mode (described below in reference to FIGS. 7-9), the SCU 302 periodically interrogates one or more microsensors and accordingly adjust the commands transmitted to one or more microstimulators.
  • FIG. 2 shows the [0034] system 300 of the present invention comprised of (1) one or more implantable devices 100 operable to sense and/or stimulate a patient's body parameter in accordance with one or more controllable operating parameters and (2) the SCU, 302. The SCU 302 is primarily comprised of (1) a housing 206, preferably sealed and configured for implantation beneath the skin of the patient's body as described in the parent application in reference to the implanted devices 100, (2) a signal transmitter 304 in the housing 206 for transmitting command signals, (3) a signal receiver 306 in the housing 206 for receiving status signals, and (4) a programmable controller 308, e.g., a microcontroller or state machine, in the housing 206 responsive to received status signals for producing command signals for transmission by the signal transmitter 304 to other implantable devices 100. The sequence of operations of the programmable controller 308 is determined by an instruction list, i.e., a program, stored in program storage 310, coupled to the programmable controller 308. While the program storage 310 can be a nonvolatile memory device, e.g., ROM, manufactured with a program corresponding to a prescribed treatment regimen, it is preferably that at least a portion of the program storage 310 be an alterable form of memory, e.g., RAM, EEPROM, etc., whose contents can be remotely altered as described further below. However, it is additionally preferable that a portion of the program storage 310 be nonvolatile so that a default program is always present. The rate at which the program contained within the program storage 310 is executed is determined by clock 312, preferably a real time clock that permits tasks to be scheduled at specified times of day.
  • The [0035] signal transmitter 304 and signal receiver 306 preferably communicate with implanted devices 100 using sound means, i.e., mechanical vibrations, using a transducer having a carrier frequency modulated by a command data signal. In a preferred embodiment, a carrier frequency of 100 KHz is used which corresponds to a frequency that freely passes through a typical body's fluids and tissues. However, such sound means that operate at any frequency, e.g., greater than 1 Hz, are also considered to be within the scope of the present invention. Alternatively, the signal transmitter 304 and signal receiver 306 can communicate using modulated AC magnetic, RF, or electric fields.
  • The clinician's [0036] programmer 172 and/or the patient control unit 174 and/or other external control devices can also communicate with the implanted devices 100, as described in the parent application, preferably using a modulated AC magnetic field. Alternatively, such external devices can communicate with the SCU 302 via a transceiver 314 coupled to the programmable controller 308. Since, in a preferred operating mode, the signal transmitter 304 and signal receiver 306 operate using sound means, a separate transceiver 314 which operates using magnetic means is used far communication with external devices. However, a single transmitter 304/receiver 306 can be used in place of transceiver 314 if a common communication means is used.
  • FIG. 3A comprises a block diagram of an exemplary implanted device [0037] 100 (as shown in FIG. 2 of the parent application) which includes a battery 104, preferably rechargeable, for powering the device for a period of time in excess of one hour and responsive to command signals from a remote device, e.g., the SCU 302. As described in the parent application, the implantable device 100 is preferably configurable to alternatively operate as a microstimulator and/or microsensor and/or microtransponder due to the commonality of most of the circuitry contained within. Such circuitry can be further expanded to permit a common block of circuitry to also perform the functions required for the SCU 302. Accordingly, FIG. 3B shows an alternative implementation of the controller circuitry 106 of FIG. 3A that is suitable for implementing a microstimulator and/or a microsensor and/or a microtransponder and/or the SCU 302. In this implementation the configuration data storage 132 can be alternatively used as the program storage 310 when the implantable device 100 is used as the SCU 302. In this implementation, XMTR 168 corresponds to the signal transmitter 304 and the RCVR 114 b corresponds to the signal receiver 306 (preferably operable using sound means via transducer 138) and the RCVR 114 a and XMTR 146 correspond to the transceiver 314 (preferably operable using magnetic means via coil 116).
  • In a preferred embodiment, the contents of the [0038] program storage 310, i.e., the software that controls the operation of the programmable controller 308, can be remotely downloaded, e.g., from the clinician's programmer 172 using data modulated onto an AC magnetic field. In this embodiment, it is preferable that the contents of the program storage 310 for each SCU 302 be protected from an inadvertent change. Accordingly, the contents of the address storage circuitry 108, i.e., the ID 303, is preferably used as a security code to confirm that the new program storage contents are destined for the SCU 302 receiving the data. This feature is significant if multiple patient's could be physically located, e.g., in adjoining beds, within the communication range of the clinician's programmer 172.
  • In a further aspect of the present invention, it is preferable that the [0039] SCU 302 be operable for an extended period of time, e.g., in excess of one hour, from an internal power supply 316. While a primary battery, i.e., a nonrechargeable battery, is suitable for this function, it is preferable that the power supply 316 include a rechargeable battery, e.g., battery 104 as described in the parent application, that can be recharged via an AC magnetic field produced external to the patient's body. Accordingly, the power supply 102 of FIG. 3A (described in detail in the parent application) is the preferred power supply 316 for the SCU 302 as well.
  • The battery-powered [0040] devices 100 of the parent invention are preferably configurable to operate in a plurality of operation modes, e.g., via a communicated command signal. In a first operation mode, device 100 is remotely configured to be a microstimulator, e.g., 100 a and 100 b. In this embodiment, controller 130 commands stimulation circuitry 110 to generate a sequence of drive pulses through electrodes 112 to stimulate tissue, e.g., a nerve, proximate to the implanted location of the microstimulator, e.g., 100 a or 100 b. In operation, a programmable pulse generator 178 and voltage multiplier 180 are configured with parameters (see Table I) corresponding to a desired pulse sequence and specifying now much to multiply the battery voltage (e.g., by summing charged capacitors or similarly charged battery portions) to generate a desired compliance voltage Vc. A first FET 182 is periodically energized to store charge into capacitor 183 (in a first direction at a low current flow rate through the body tissue) and a second FET 184 is periodically energized to discharge capacitor 183 in an opposing direction at a higher current flow rate which stimulates a nearby nerve. Alternatively, electrodes can be selected that will form an equivalent capacitor within the body tissue.
    TABLE I
    Stimulation Parameters
    Current: continuous current charging of
    storage capacitor
    Charging currents: 1, 3, 10, 30, 100, 250, 500 μa
    Current Range: 0.8 to 40 ma in nominally 3.2% steps
    Compliance Voltage: selectable, 3-24 volts in 3 volt
    steps
    Pulse Frequency (PPS): 1 to 5000 PPS in nominally 30% steps
    Pulse Width: 5 to 2000 μs in nominally 10% steps
    Burst On Time (BON): 1 ms to 24 hours in nominally 20%
    steps
    Burst Off Time (BOF): 1 ms to 24 hours in nominally 20%
    steps
    Triggered Delay to BON: either selected BOF or pulse width
    Burst Repeat Interval: 1 ms to 24 hours in nominally 20%
    steps
    Ramp On Time: 0.1 to 100 seconds (1, 2, 5, 10
    steps)
    Ramp Off Time: 0.1 to 100 seconds (1, 2, 5, 10
    steps)
  • In a next operation mode, the battery-powered [0041] implantable device 100 can be configured to operate as a microsensor, e.g., 100 c, that can sense one or more physiological or biological parameters in the implanted environment of the device. In accordance with a preferred mode of operation, the system control unit 302 periodically requests the sensed data from each microsensor 100 c using its ID stored in address storage 108, and responsively sends command signals to microstimulators, e.g., 100 a and 100 b, adjusted accordingly to the sensed data. For example, sensor circuitry 188 can coupled to the electrodes 112 to sense or otherwise used to measure a biological parameter, e.g., temperature, glucose level, or O2 content and provided the sensed data to the controller circuitry 106. Preferably, the sensor circuitry includes a programmable bandpass filter and an analog to digital (A/D) converter that can sense and accordingly convert the voltage levels across the electrodes 112 into a digital quantity. Alternatively, the sensor circuitry can include one or more sense amplifiers to determine if the measured voltage exceeds a threshold voltage value or is within a specified voltage range. Furthermore, the sensor circuitry 188 can be configurable to include integration circuitry to further process the sensed voltage. The operation modes of the sensor circuitry 188 is remotely programable via the devices communication interface as shown below in Table II.
    TABLE II
    Sensing Parameters
    Input voltage range: 5 μv to 1 V
    Bandpass filter rolloff: 24 dB
    Low frequency cutoff choices: 3, 10, 30, 100, 300, 1000 Hz
    High frequency cutoff choices: 3, 10, 30, 100, 300, 1000 Hz
    Integrator frequency choices: 1 PPS to 100 PPS
    Amplitude threshold
    4 bits of resolution
    for detection choices:
  • Additionally, the sensing capabilities of a microsensor include the capability to monitor the battery status via path [0042] 124 from the charging circuit 122 and can additionally include using the ultrasonic transducer 138 or the coil 116 to respectively measure the magnetic or ultrasonic signal magnitudes (or transit durations) of signals transmitted between a pair of implanted devices and thus determine the relative locations of these devices. This information can be used to determine the amount of body movement, e.g., the amount that an elbow or finger is bent, and thus form a portion of a closed loop motion control system.
  • In another operation mode, the battery-powered [0043] implantable device 100 can be configured to operate as a microtransponder, e.g., 100 d. In this operation mode, the microtransponder receives (via the aforementioned receiver means, e.g., AC magnetic, sonic, RF or electric) a first command signal from the SCU 302 and retransmits this signal (preferably after reformatting) to other implanted devices (e.g., microstimulators, microsensors, and/or microtransponders) using the aforementioned transmitter means (e.g., magnetic, sonic, RF or electric). While a microtransponder may receive one mode of command signal, e.g., it may retransmit the signal in another mode, e.g., ultrasonic. For example, clinician's programmer 172 may emit a modulated magnetic signal using a magnetic emitter 190 to program/command the implanted devices 100. However, the magnitude of the emitted signal may not be sufficient to be successfully received by all of the implanted devices 100. As such, a microtransponder 100 d may receive the modulated magnetic signal and retransmit it (preferably after reformatting) as a modulated ultrasonic signal which can pass through the body with fewer restrictions. In another exemplary use, the patient control unit 174 may need to monitor a microsensor 100 c in a patient's foot. Despite the efficiency of ultrasonic communication in a patient's body, an ultrasonic signal could still be insufficient to pass from a patient's foot to a patient's wrist (the typical location of the patient control unit 174). As such, a microtransponder 100 d could be implanted in the patient's torso to improve the communication link.
  • FIG. 4 shows the basic format of an [0044] exemplary message 192 for communicating with the aforementioned battery-powered devices 100, all of which are preconfigured with an address (ID), preferably unique to that device, in their identification storage 108 to operate in one or more of the following modes (1) for nerve stimulation, i.e., as a microstimulator, (2) for biological parameter monitoring, i.e., as a microsensor, and/or (3) for retransmitting received signals after reformatting to other implanted devices, i.e., as a microtransponder. The command message 192 is primarily comprised of a (1) start portion 194 (one or more bits to signify the start of the message and to synchronize the bit timing between transmitters and receivers, (2) a mode portion 196 (designating the operating mode, e.g., microstimulator, microsensor, microtransponder, or group mode), (3) an address (ID) portion 198 (corresponding to either the identification address 108 or a programmed group ID), (4) a data field portion 200 (containing command data for the prescribed operation), (5) an error checking portion 202 (for ensuring the validity of the message 192, e.g., by use of a parity bit), and (6) a stop portion 204 (for designating the end of the message 192). The basic definition of these fields are shown below in Table III. Using these definitions, each device can be separately configured, controlled and/or sensed as part of a system or controlling one or more neural pathways within a patient's body.
    TABLE III
    Message Data Fields
    MODE ADDRESS (ID)
    00 = Stimulator 8 bit identification address
    01 = Sensor 8 bit identification address
    02 = Transponder 4 bit identification address
    03 = Group 4 bit group identification
    address
    Data Field Portion
    Program/Stimulate = select operating mode
    Parameter/
    Preconfiguration
    Select = select programmable parameter in
    program mode or preconfigured
    stimulation or sensing parameter
    in other modes
    Parameter Value = program value
  • Additionally, each [0045] device 100 can be programmed with a group ID (e.g., a 4 bit value) which is stored in its configuration data storage 132. When a device 100, e.g., a microstimulator, receives a group ID message that matches its stored group ID, it responds as if the message was directed to its identification address 108. Accordingly, a plurality of microstimulators, e.g., 100 a and 100 b, can be commanded with a single message. This mode is of particular use when precise timing is desired among the stimulation of a group of nerves.
  • The following describes exemplary commands, corresponding to the [0046] command message 192 of FIG. 4, which demonstrate some of the remote control/sensing capabilities of the system of devices which comprise the present invention:
  • Write Command—Set a microstimulator/microsensor specified in the [0047] address field 198 to the designated parameter value.
  • Group Write Command—Set the microstimulators/microsensors within the group specified in the [0048] address field 198 to the designated parameter value.
  • Stimulate Command—Enable a sequence of drive pulses from the microstimulator specified in the [0049] address field 198 according to previously programmed and/or default values.
  • Group Stimulate Command—Enable a sequence of drive pulses from the microstimulators within the group specified in the [0050] address field 198 according to previously programmed and/or default values.
  • Unit Off Command—Disable the output of the microstimulator specified in the [0051] address field 198.
  • Group Stimulate Command—Disable the output of the microstimulators within the group specified in the [0052] address field 198.
  • Read Command—Cause the microsensor designated in the [0053] address field 198 to read the previously programmed and/or default sensor value according to previously programmed and/or default values.
  • Read Battery Status Command—Cause the microsensor designated in the [0054] address field 198 to return its battery status.
  • Define Group Command—Cause the microstimulator/microsensor designated in the [0055] address field 198 to be assigned to the group defined in the microstimulator data field 200.
  • Set Telemetry Mode Command—Configure the microtransponder designated in the [0056] address field 198 as to its input mode (e.g., AC magnetic, sonic, etc.), output mode (e.g., AC magnetic, sonic, etc.), message length, etc.
  • Status Reply Command—Return the requested status/sensor data to the requesting unit, e.g., the SCU. [0057]
  • Download Program Command—Download program/safe harbor routines to the device, e.g., SCU, microstimulator, etc., specified in the [0058] address field 198.
  • FIG. 5 shows a block diagram of an exemplary open loop control program, i.e., a [0059] task scheduler 320, for controlling/monitoring a body function/parameter. In this process, the programmable controller 308 is responsive to the clock 312 (preferably crystal controlled to thus permit real time scheduling) in determining when to perform any of a plurality of tasks. In this exemplary flow chart, the programmable controller 308 first determines in block 322 if is now at a time designated as TEVENT1 (or at least within a sampling error of that time), e.g., at 1:00 AM. If so, the programmable controller 308 transmits a designated command to microstimulator A (STA) in block 324. In this example, the control program continues where commands are sent to a plurality of stimulators and concludes in block 326 where a designated command is sent to microstimulator X (STX). Such a subprocess, e.g., a subroutine, is typically used when multiple portions of body tissue require stimulation, e.g, stimulating a plurality of muscle groups in a paralyzed limb to avoid atrophy. The task scheduler 320 continues through multiple time event detection blocks until in block 328 it determines whether the time TEVENTM has arrived. If so, the process continues at block 330 where, in this case, a single command is sent to microstimulator M (STM). Similarly, in block 332 the task scheduler 320 determines when it is the scheduled time, i.e., TEVENT0, to execute a status request from microsensor A (SEA). Is so, a subprocess, e.g., a subroutine, commences at block 334 where a command is sent to microsensor A (SEA) to request sensor data and/or specify sensing criteria. Microsensor A (SEA) does not instantaneously respond. Accordingly, the programmable controller 308 waits for a response in block 336. In block 338, the returned sensor status data from microsensor A (SEA) is stored in a portion of the memory, e.g., a volatile portion of the program storage 310, of the programmable controller 308. The task scheduler 320 can be a programmed sequence, i.e., defined in software stored in the program storage 310, or, alternatively, a predefined function controlled by a table of parameters similarly stored in the program storage 310. A similar process can be used where the SCU 302 periodically interrogates each implantable device 100 to determine its battery status.
  • FIG. 6 shows an exemplary use of an optional translation table [0060] 340 for communicating between the SCU 302 and microstimulators, e.g., 100 a, and/or microsensors, e.g., 100 c, via microtransponders, e.g., 100 d. A microtransponder, e.g., 100 d, is used when the communication range of the SCU 302 is insufficient to reliably communicate with other implanted devices 100. In this case, the SCU 302 instead directs a data message, i.e., a data packet, to an intermediary microtransponder, e.g., 100 d, which retransmits the data packet to a destination device 100. In an exemplary implementation, the translation table 340 contains pairs of corresponding entries, i.e., first entries 342 corresponding to destination addresses and second entries 344 corresponding to the intermediary microtransponder addresses. When the SCU 302 determines, e.g., according to a timed event designated in the program storage 310, that a command is to be sent to a designated destination device (see block 346), the SCU 302 searches the first entries 342 of the translation table 340, for the destination device address, e.g., STM. The SCU 302 then fetches the corresponding second table entry 344 in block 348 and transmits the command to that address. When the second table entry 344 is identical to its corresponding first table entry 342, the SCU 302 transmits commands directly to the implanted device 100. However, when the second table entry 344, e.g., TN, is different from the first table entry 342, e.g., STM, the SCU 302 transmits commands via an intermediary microtransponder, e.g., 100 d. The use of the translation table 340 is optional since the intermediary addresses can, instead, be programmed directly into a control program contained in the program storage 310. However, it is preferable to use such a translation table 340 in that communications can be redirected on the fly by just reprogramming the translation table 340 to take advantage of implanted transponders as required, e.g., if communications should degrade and become unreliable. The translation table 340 is preferably contained in programmable memory, e.g., RAM or EPROM, and can be a portion of the program storage 310. While the translation table 340 can be remotely programmed, e.g., via a modulated signal from the clinician's programmer 172, it is also envisioned that the SCU 302 can reprogram the translation table 340 if the communications degrade.
  • FIG. 7 is an exemplary block diagram showing the use of the system of the present invention to perform closed loop control of a body function. In [0061] block 352, the SCU 302 requests status from microsensor A (SEA). The SCU 302, in block 354, then determines whether a current command given to a microstimulator is satisfactory and, if necessary, determines a new command and transmits the new command to the microstimulator A in block 356. For example, if microsensor A (SEA) is reading a voltage corresponding to a pressure generated by the stimulation of a muscle, the SCU 302 could transmit a command to microstimulator A (STA) to adjust the sequence of drive pulses, e.g., in magnitude, duty cycle, etc., and accordingly change the voltage sensed by microsensor A (SEA). Accordingly, closed loop, i.e., feedback, control is accomplished. The characteristics of the feedback (position, integral, derivative (PID)) control are preferably program controlled by the SCU 302 according to the control program contained in program storage 310.
  • FIG. 8 shows an exemplary injury treatable by embodiments of the [0062] present system 300. In this exemplary injury, the neural pathway has been damaged, e.g, severed, just above the a patient's left elbow. The goal of this exemplary system is to bypass the damaged neural pathway to permit the patient to regain control of the left hand. An SCU 302 is implanted within the patient's torso to control plurality of stimulators, ST1-ST3, implanted proximate to the muscles respectively controlling the patient's thumb and fingers. Additionally, microsensor 1 (SE1) is implanted proximate to an undamaged nerve portion where it can sense a signal generated from the patient's brain when the patient wants hand closure. Optional microsensor 2 (SE2) is implanted in a portion of the patient's hand where it can sense a signal corresponding to stimulation/motion of the patient's pinky finger and microsensor 3 (SE3) is implanted and configured to measure a signal corresponding to grip pressure generated when the fingers of the patient's hand are closed. Additionally, an optional microtransponder (T1) is shown which can be used to improve the communication between the SCU 302 and the implanted devices.
  • FIG. 9 shows an exemplary flow chart for the operation of the [0063] SCU 302 in association with the implanted devices in the exemplary system of FIG. 8. In block 360, the SCU 302 interrogates microsensor 1 (SE1) to determine if the patient is requesting actuation of his fingers. If not, a command is transmitted in block 362 to all of the stimulators (ST1-ST3) to open the patient's hand, i.e., to de-energize the muscles which close the patient's fingers. If microsensor 1 (SE1) senses a signal to actuate the patient's fingers, the SCU 302 determines in block 364 whether the stimulators ST1-ST3 are currently energized, i.e., generating a sequence of drive pulses. If not, the SCU 302 executes instructions to energize the simulators. In a first optional path 366, each of the stimulators are simultaneously (subject to formatting and transmission delays) commanded to energize in block 366 a. However, the command signal given to each one specifies a different start delay time (using the BON parameter). Accordingly, there is a stagger between the actuation/closing of each finger.
  • In a second [0064] optional path 368, the microstimulators are consecutively energized by a delay Δ. Thus, microstimulator 1 (ST1) is energized in block 368 a, a delay is executed within the SCU 302 in block 368 b, and so on for all of the microstimulators. Accordingly, paths 366 and 368 perform essentially the same function. However, in path 366 the interdevice timing is performed by the clocks within each implanted device 100 while in math 368, the SCU 302 is responsible for providing the interdevice timing.
  • In [0065] path 370, the SCU 302 actuates a first microstimulator (ST1) in block 370 a and waits in block 370 b for its corresponding muscle to be actuated, as determined by microsensor 2 (SE2), before actuating the remaining stimulators (ST2-ST3) in block 370 c. This implementation could provide more coordinated movement in some situations.
  • Once the stimulators have been energized, as determined in [0066] block 364, closed loop grip pressure control is performed in blocks 372 a and 372 b by periodically reading the status of microsensor 3 (SE3) and adjusting the commands given to the stimulators (ST1-ST3) accordingly. Consequently, this exemplary system has enabled the patient to regain control of his hand including coordinated motion and grip pressure control of the patient's fingers.
  • Referring again to FIG. 3A, a [0067] magnetic sensor 186 is shown. In the parent application, it was shown that such a sensor 186 could be used to disable the operation of an implanted device 100, e.g., to stop the operation of such devices in an emergency situation, in response to a DC magnetic field, preferably from an externally positioned safety magnet 187. A further implementation is disclosed herein. The magnetic sensor 186 can be implemented using various devices. Exemplary of such devices are devices manufactured by Nonvolatile Electronics, Inc. (e.g., their AA, AB, AC, AD, or AG series), Hall effect sensors, and subminiature reed switches. Such miniature devices are configurable to be placed within the housing of the disclosed SCU 302 and implantable devices 100. While essentially passive magnetic sensors, e.g., reed switches, are possible, the remaining devices include active circuitry that consumes power during detection of the DC magnetic field. Accordingly, it is preferred that controller circuitry 302 periodically, e.g., once a second, provide power the magnetic sensor 186 and sample the sensor's output signal 374 during that sampling period.
  • In a preferred implementation of the [0068] SCU 302, the programmable controller 308 is a microcontroller operating under software control wherein the software is located within the program storage 310. The SCU 302 preferably includes an input 376, e.g., a non maskable interrupt (NMI), which causes a safe harbor subroutine 378, preferably located within the program storage 310, to be executed. Additionally, failure or potential failure modes, e.g., low voltage or over temperature conditions, can be used to cause the safe harbor subroutine 378 to be executed. Typically, such a subroutine could cause a sequence of commands to be transmitted to set each microstimulator into a safe condition for the particular patient configuration, typically disabling each microstimulator. Alternatively, the safe harbor condition could be to set certain stimulators to generate a prescribed sequence of drive pulses. Preferably, the safe harbor subroutine 378 can be downloaded from an external device, e.g., the clinician's programmer 172, into the program storage 310, a nonvolatile storage device. Additionally, it is preferable that, should the programmable contents of the program storage be lost, e.g., from a power failure, a default safe harbor subroutine be used instead. This default subroutine preferably stored in nonvolatile storage that is not user programmable, e.g., ROM, that is otherwise a portion of the program storage 310. This default subroutine is preferably general purpose and typically is limited to commands that turn off all potential stimulators.
  • Alternatively, such programmable [0069] safe harbor subroutines 378 can exist in the implanted stimulators 100. Accordingly, a safe harbor subroutine could be individually programmed into each microstimulator that is customized for the environments of that microstimulator and a safe harbor subroutine for the SCU 302 could then be designated that disables the SCU 302, i.e. causes the SCU 302 to not issue subsequent commands to other implanted devices 100.
  • FIGS. [0070] 10A and 10BD show two side cutaway views of the presently preferred construction of the sealed housing 206, the battery 104 and the circuitry (implemented on one or more IC chips 216 to implement electronic portions or the SCU 302) contained within. In this presently preferred construction, the housing 206 is comprised of an insulating ceramic tube 260 brazed onto a first end cap forming electrode 112 a via a braze 262. At the other end of the ceramic tube 260 is a metal ring 264 that is also brazed onto the ceramic tube 260. The circuitry within, i.e., a capacitor 183 (used when in a microstimulator mode), battery 104, IC chips 216, and a spring 266 is attached to an opposing second end cap forming electrode 112 b. A drop of conductive epoxy is used to glue the capacitor 183 to the end cap 112 a and is held in position by spring 266 as the glue takes hold. Preferably, the IC chips 216 are mounted on a circuit board 268 over which half circular longitudinal ferrite slates 270 are attached. The coil 116 is wrapped around the ferrite plates 270 and attached to IC chips 216. A getter 272, mounted surrounding the spring 266, is preferably used to increase the hermeticity of the SCU 302 by absorbing water introduced therein. An exemplary getter 272 absorbs 70 times its volume in water. While holding the circuitry and the end cap 112 b together, one can laser weld the end cap 112 b to the ring 264. Additionally, a platinum, iridium, or platinum-iridium disk or plate 274 is preferably welded to the end caps of the SCU 302 to minimize the impedance of the connection to the body tissue.
  • An [0071] exemplary battery 104 is described more fully below in connection with the description of FIG. 11. Preferably, the battery 104 is made from appropriate materials so as to provide a power capacity of at least 1 microwatt-hour, preferably constructed from a battery having an energy density of about 240 mW-Hr/cm3. A Li—I battery advantageously provides such an energy density. Alternatively, an Li—I—Sn battery provides an energy density up to 360 mW-Hr/cm3. Any of these batteries, or other batteries providing a power capacity of at least 1 microwatt-hour may be used with implanted devices of the present invention.
  • The battery voltage V of an exemplary battery is nominally 3.6 volts, which is more than adequate for operating the CMOS circuits preferably used to implement the IC chip(s) [0072] 216, and/or other electronic circuitry, within the SCU 302. The battery voltage V, in general, is preferably not allowed to discharge below about 2.55 volts, or permanent damage may result. Similarly, the battery 104 should preferably not be charged to a level above about 4.2 volts, or else permanent damage may result. Hence, a charging circuit 122 (discussed in the parent application) is used to avoid any potentially damaging discharge or overcharge.
  • The [0073] battery 104 may take many forms, any of which may be used so long as the battery can be made to fit within the small volume available. As previously discussed, the battery 104 may be either a primary battery or a rechargeable battery. A primary battery offers the advantage of a longer life for a given energy output but presents the disadvantage of not being rechargeable (which means once its energy has been used up, the implanted device no longer functions). However, for many applications, such as one-time-only muscle rehabilitation regimens applied to damaged or weakened muscle tissue, the SCU 302 and/or devices 100 need only be used for a short time (after which they can be explanted and discarded, or simply left implanted as benign medical devices). For other applications, a rechargeable battery is clearly the preferred type of energy choice, as the tissue stimulation provided by the microstimulator is of a recurring nature.
  • The considerations relating to using a rechargeable battery as the [0074] battery 104 of the implantable device 100 are presented, inter alia, in the book, Rechargeable Batteries, Applications Handbook, EDN Series for Design Engineers, Technical Marketing Staff of Gates Energy Products, Inc. (Butterworth-Heinemann 1992). The basic considerations for any rechargeable battery relate to high energy density and long cycle life. Lithium based batteries, while historically used primarily as a nonrechargeable battery, have in recent years appeared commercially as rechargeable batteries. Lithium-based batteries typically offer an energy density of from 240 mW-Hr/cm3 to 360 mW-Hr/cm3. In general, the higher the energy density the better, but any battery construction exhibiting an energy density resulting in a power capacity greater than 1 microwatt-hour is suitable for the present invention.
  • One of the more difficult hurdles facing the use of a [0075] battery 104 within the SCU 302 relates to the relatively small size or volume inside the housing 206 within which the battery must be inserted. A typical SCU 302 made in accordance with the present invention is no larger than about 60 mm long and 8 mm in diameter, preferably no larger than 60 mm long and 6 mm in diameter, and includes even smaller embodiments, e.g., 15 mm long with an O.D. of 2.2 mm (resulting in an I.D. of about 2 mm). When one considers that only about ¼ to ½ of the available volume within the device housing 206 is available for the battery, one begins to appreciate more fully how little volume, and thus how little battery storage capacity, is available for the SCU 302.
  • FIG. 11 shows an [0076] exemplary battery 104 typical of those disclosed in the parent application. Specifically, a parallel-connected cylindrical electrode embodiment is shown where each cylindrical electrode includes a gap or slit 242; with the cylindrical electrodes 222 and 224 on each side of the gap 242 forming a common connection point for tabs 244 and 246 which serve as the electrical terminals for the battery. The electrodes 222 and 224 are separated by a suitable separator 248. The gap 242 minimizes the flow of eddy currents in the electrodes. For this embodiment, there are four concentric cylindrical electrodes 222, the outer one (largest diameter) of which may function as the battery case 234, and three concentric electrodes 224 interleaved between the electrodes 222, with six concentric cylindrical separator layers 248 separating each electrode 222 or 224 from the adjacent electrodes.
  • Accordingly, a preferred embodiment of the present invention is comprised of an implanted [0077] SCU 302 and a plurality of implanted devices 100, each of which contains its own rechargeable battery 104. As such, a patient is essentially independent of any external apparatus between battery chargings (which generally occur no more often than once an hour). However, for some treatment regimen, it may be adequate to use a power supply analogous to that described in U.S. Pat. No. 5,324,316 that only provides power while an external AC magnetic field is being provided, e.g., from charger 118. Additionally, it may be desired, e.g., from a cost standpoint, to implement the SCU 302 as an external device, e.g., within a watch-shaped housing that can be attached to a patient's wrist in a similar manner to the patient control unit 174.
  • The power consumption of the [0078] SCU 302 is primarily dependent upon the circuitry implementation, preferably CMOS, the circuitry complexity and the clock speed. For a simple system, a CMOS implemented state machine will be sufficient to provide the required capabilities of the programmable controller 308. However, for more complex systems, e.g., a system where an SCU 302 controls a large number of implanted devices 100 in a closed loop manner, a microcontroller may be required. As the complexity of such microcontrollers increases (along with its transistor count), so does its power consumption. Accordingly, a larger battery having a capacity of 1 watt-hour is preferred. While a primary battery is possible, it is preferable that a rechargeable battery be used. Such larger batteries will require a larger volume and accordingly, cannot be placed in the injectable housing described above. However, a surgically implantable device within a larger sealed housing, e.g., having at least one dimension in excess of 1 inch, will serve this purpose when used in place of the previously discussed injectable housing 206. FIG. 12 shows an exemplary implantable housing 380 suitable for such a device.
  • While the invention herein disclosed has been described by means of specific embodiments and applications thereof, numerous modifications and variations could be made thereto by those skilled in the art without departing from the scope of the invention set forth in the claims. For example, a system including multiple SCUs, e.g., one external and one internal, is considered to be within the scope of the present invention. Additionally, while the use of a single communication channel for communication between one or more SCUs and the other implanted devices has been described, a system implemented using multiple communication channels, e.g., a first sonic channel at a first carrier frequency and a second sonic channel at a second carrier frequency, is also considered to be within the scope of the present invention. [0079]

Claims (33)

We claim:
1. A system for monitoring and/or affecting at least one parameter of a patient's body, said system comprising:
at least one implantable device operable to sense and/or stimulate a patient's body parameter in accordance with one or more controllable operating parameters; and
a system control unit for controlling said controllable operating parameters, said system control unit comprising:
a sealed elongate housing configured for implantation in a patient's body;
a signal transmitter in said housing for transmitting command signals;
a signal receiver in said housing for receiving status signals; and
a programmable controller in said housing responsive to received status signals for producing command signals for transmission by said signal transmitter to said implantable devices.
2. The system of claim 1 wherein said sealed housing has an axial dimension of less than 60 mm and a lateral dimension of less than 6 mm suitable for injection into the patient's body.
3. The system of claim A1 comprising at least one said implantable device operable as a sensor and at least one said implantable operable as a stimulator and wherein said controller is responsive to status data signals received from said sensor for generating said addressable command data signals to said stimulator to perform closed loop control of the operation of said stimulator.
4. The system of claim 1 wherein said system control unit additionally comprises a power source contained within said sealed housing for providing operating power to said data signal transmitter, said data signal receiver, and said programmable controller.
5. The system of claim 1 wherein said signal receiver includes a coil responsive to status signals defined by a modulated magnetic field.
6. The system of claim 1 wherein said signal receiver includes a transducer responsible to status signals defined by a modulated ultrasonic signal.
7. The system of claim 1 wherein said signal transmitter includes means for transmitting command signals in the form of a modulated magnetic field.
8. The system of claim 1 wherein said signal transmitter includes means for transmitting command signals in the form of a modulated ultrasonic signal.
9. The system of claim 1 wherein said system control unit additionally includes:
at least one electrode;
sensor/stimulator circuitry; and wherein
said sensor stimulator circuitry is configurable to generate a data signal representative of an electrical signal conducted by said electrode and/or supply a sequence of drive pulses to said electrode.
10. The system of claim 1 wherein each of said implantable devices includes a power source having a capacity of at least 1 microwatt-hour.
11. The system of claim 10 wherein each said implantable device includes means for monitoring status of its power source and said system control unit is configured to transmit command signals to each said implantable device and to responsively receive status signals corresponding to said power source status.
12. The system of claim 1 further including:
program storage means in said housing for specifying the operation of said programmable controller; and
means to modify said program storage means in response to signals received by said signal receiver.
13. The system or claim 12 wherein said program storage means includes means to cause said system control unit to transmit a programmable list of command signals to said implantable devices.
14. The system of claim 13 wherein said means to cause said system control unit to transmit a programmable list of command signals includes:
a magnetic sensor for generating a signal responsive to a DC magnetic field; and wherein
said programmable list of command signals is transmitted in response to said magnetic sensor signal.
15. A system control unit configured for implantation in a patient's body for controlling/monitoring the operation of one or more other implantable addressable devices, said system control unit comprising:
a sealed elongate housing;
a data signal transmitter for wireless transmission of command data signals;
a data signal receiver for wireless reception of status data signals;
a controller capable of accepting status data signals from said data signal receiver and sending addressable command data signals to said data signal transmitter in response thereto to control and/or monitor the operation of one or more other implantable devices in accordance with one or more controllable operating parameters;
program storage means for specifying the operation of said controller; and wherein
said data signal transmitter, data signal receiver, said controller, and said program storage means are disposed within said sealed housing.
16. The system control unit of claim 15 wherein said sealed housing has an axial dimension of less than 60 mm and a lateral dimension of less than 6 mm suitable for injection into the patient's body.
17. The system control unit of claim 15 additionally comprising a power source contained within said sealed housing for providing operating power to said data signal transmitter, said data signal receiver, said controller, and said program storage means.
18. The system control unit of claim 15 wherein said data signal receiver includes a coil responsive to a status data signal defined by a modulated magnetic field.
19. The system control unit of claim 15 wherein said data signal receiver includes a transducer responsive to a status data signal defined by a modulated ultrasonic signal.
20. The system control unit of claim 15 wherein said transmitter includes means for transmitting a command data signal in the form of a modulated magnetic field.
21. The system control unit of claim 15 wherein said transmitter includes means for transmitting a command data signal in the form of a modulated ultrasonic signal.
22. The system control unit of claim 15 further including means to modify said program storage means in response to signals received by said data signal receiver.
23. The system control unit of claim 15 additionally including:
at least one electrode;
sensor/stimulator circuitry; and wherein
said sensor stimulator circuitry is configurable to generate a data signal representative of an electrical signal conducted by said electrode and/or supply a sequence of drive pulses to said electrode.
24. A system for monitoring and/or affecting at least one parameter of a patient's body, said system comprising:
a system control unit positioned outside of the patient's body comprising:
means for providing wireless transmission of command data signals;
means for providing wireless reception of status data signals; and
means capable of accepting status data signals from said data signal receiver and sending addressable command data signals to said data signal transmitter in response thereto to control and/or monitor the operation of one or more implantable devices; and
at least one addressable device configured for implantation in a patient's body responsive to said command data signals, said implantable devices selected from one or more of the following groups:
stimulators having at least one electrode configured to produce an electrical current for stimulating body tissue to affect a parameter of the patient's body; and
sensors having at least one electrode configured to produce a data signal corresponding to an electrical signal conducted by said electrode and representative of a parameter of the patient's body; and wherein
each of said implantable devices includes a power source having a power capacity of at least 1 microwatt-hour.
25. The system of claim 24 wherein said implantable devices include:
at least one stimulator and at least one sensor; and wherein
said system control unit is responsive to status data signals received from said sensor for generating said addressable command data signals to said stimulator to perform closed loop control of the operation of said stimulator.
26. The system of claim 24 wherein said groups of implantable devices further include transponders for transmitting a data signal related to a command signal received by said transponder.
27. The system of claim 24 wherein said implantable devices include:
at least one stimulator, at least one sensor and at least one transponder; and wherein
said system control unit is responsive to status data signals received from said sensor for generating said addressable command data signals to said stimulator to perform closed loop control of the operation of said stimulator.
28. The system of claim 27 wherein said status data signal received from said sensor is received via said transponder.
29. The system of claim 27 wherein said stimulator is responsive to said command data signals received via said transponder.
30. The system of claim 24 wherein said wireless reception means includes a coil responsive to a status data signal defined by a modulated magnetic field.
31. The system of claim 24 wherein said wireless reception means includes a transducer responsive to a status data signal defined by a modulated ultrasonic signal.
32. The system of claim 24 wherein said wireless transmission means includes means for transmitting a command data signal in the form of a modulated magnetic field.
33. The system of claim 24 wherein said wireless transmission means includes means for transmitting a command data signal in the form of a modulated ultrasonic signal.
US10/391,424 1997-02-26 2003-03-17 System of implantable devices for monitoring and/or affecting body parameters Abandoned US20040011366A1 (en)

Priority Applications (8)

Application Number Priority Date Filing Date Title
US10/391,424 US20040011366A1 (en) 1997-02-26 2003-03-17 System of implantable devices for monitoring and/or affecting body parameters
US10/719,715 US7114502B2 (en) 1997-02-26 2003-11-21 Battery-powered patient implantable device
US10/920,570 US8555894B2 (en) 1997-02-26 2004-08-18 System for monitoring temperature
US10/920,554 US8684009B2 (en) 1997-02-26 2004-08-18 System for determining relative distance(s) and/or angle(s) between at least two points
US10/997,398 US20050075682A1 (en) 1997-02-26 2004-11-24 Neural device for sensing temperature
US11/004,758 US7460911B2 (en) 1997-02-26 2004-12-03 System and method suitable for treatment of a patient with a neurological deficit by sequentially stimulating neural pathways using a system of discrete implantable medical devices
US11/187,290 US7513257B2 (en) 1997-02-26 2005-07-21 System of implantable devices for monitoring and/or affecting body parameters
US14/197,797 US9750428B2 (en) 1997-02-26 2014-03-05 System for deteriming relative distance(s) and/or angel(s) between at least two points

Applications Claiming Priority (6)

Application Number Priority Date Filing Date Title
US3916497P 1997-02-26 1997-02-26
US4244797P 1997-03-27 1997-03-27
US09/030,106 US6185452B1 (en) 1997-02-26 1998-02-25 Battery-powered patient implantable device
US09/048,827 US6164284A (en) 1997-02-26 1998-03-25 System of implantable devices for monitoring and/or affecting body parameters
US09/677,384 US6564807B1 (en) 1997-02-26 2000-09-30 System of implantable devices for monitoring and/or affecting body parameters
US10/391,424 US20040011366A1 (en) 1997-02-26 2003-03-17 System of implantable devices for monitoring and/or affecting body parameters

Related Parent Applications (1)

Application Number Title Priority Date Filing Date
US09/677,384 Division US6564807B1 (en) 1997-02-26 2000-09-30 System of implantable devices for monitoring and/or affecting body parameters

Related Child Applications (5)

Application Number Title Priority Date Filing Date
US10/719,715 Continuation-In-Part US7114502B2 (en) 1997-02-26 2003-11-21 Battery-powered patient implantable device
US10/920,554 Continuation-In-Part US8684009B2 (en) 1997-02-26 2004-08-18 System for determining relative distance(s) and/or angle(s) between at least two points
US10/920,570 Continuation-In-Part US8555894B2 (en) 1997-02-26 2004-08-18 System for monitoring temperature
US11/004,758 Continuation-In-Part US7460911B2 (en) 1997-02-26 2004-12-03 System and method suitable for treatment of a patient with a neurological deficit by sequentially stimulating neural pathways using a system of discrete implantable medical devices
US11/187,290 Continuation US7513257B2 (en) 1997-02-26 2005-07-21 System of implantable devices for monitoring and/or affecting body parameters

Publications (1)

Publication Number Publication Date
US20040011366A1 true US20040011366A1 (en) 2004-01-22

Family

ID=27365508

Family Applications (4)

Application Number Title Priority Date Filing Date
US09/048,827 Expired - Lifetime US6164284A (en) 1997-02-26 1998-03-25 System of implantable devices for monitoring and/or affecting body parameters
US09/677,384 Expired - Lifetime US6564807B1 (en) 1997-02-26 2000-09-30 System of implantable devices for monitoring and/or affecting body parameters
US10/391,424 Abandoned US20040011366A1 (en) 1997-02-26 2003-03-17 System of implantable devices for monitoring and/or affecting body parameters
US11/187,290 Expired - Fee Related US7513257B2 (en) 1997-02-26 2005-07-21 System of implantable devices for monitoring and/or affecting body parameters

Family Applications Before (2)

Application Number Title Priority Date Filing Date
US09/048,827 Expired - Lifetime US6164284A (en) 1997-02-26 1998-03-25 System of implantable devices for monitoring and/or affecting body parameters
US09/677,384 Expired - Lifetime US6564807B1 (en) 1997-02-26 2000-09-30 System of implantable devices for monitoring and/or affecting body parameters

Family Applications After (1)

Application Number Title Priority Date Filing Date
US11/187,290 Expired - Fee Related US7513257B2 (en) 1997-02-26 2005-07-21 System of implantable devices for monitoring and/or affecting body parameters

Country Status (1)

Country Link
US (4) US6164284A (en)

Cited By (38)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20050032511A1 (en) * 2003-08-07 2005-02-10 Cardiac Pacemakers, Inc. Wireless firmware download to an external device
US20050075682A1 (en) * 1997-02-26 2005-04-07 Schulman Joseph H. Neural device for sensing temperature
US20050137648A1 (en) * 1997-02-26 2005-06-23 Gregoire Cosendai System and method suitable for treatment of a patient with a neurological deficit by sequentially stimulating neural pathways using a system of discrete implantable medical devices
US20060009856A1 (en) * 2004-06-29 2006-01-12 Sherman Jason T System and method for bidirectional communication with an implantable medical device using an implant component as an antenna
US20060140139A1 (en) * 2004-12-29 2006-06-29 Disilvestro Mark R Medical device communications network
WO2006113654A1 (en) * 2005-04-18 2006-10-26 Bioness Development, Llc System and related method for determining a measurement between locations on a body
US20070088398A1 (en) * 2005-10-14 2007-04-19 Jacobson Peter M Leadless cardiac pacemaker triggered by conductive communication
US20070106175A1 (en) * 2004-03-25 2007-05-10 Akio Uchiyama In-vivo information acquisition apparatus and in-vivo information acquisition apparatus system
US20080132882A1 (en) * 2006-11-30 2008-06-05 Howmedica Osteonics Corp. Orthopedic instruments with RFID
US20080211302A1 (en) * 2007-02-09 2008-09-04 Takashi Hirota Assist device
US20090069865A1 (en) * 2006-05-01 2009-03-12 Eyal Lasko Functional electrical stimulation systems
US20090082828A1 (en) * 2007-09-20 2009-03-26 Alan Ostroff Leadless Cardiac Pacemaker with Secondary Fixation Capability
US20100168622A1 (en) * 2005-11-16 2010-07-01 Amit Dar Sensor device for gait enhancement
US20100198288A1 (en) * 2009-02-02 2010-08-05 Alan Ostroff Leadless Cardiac Pacemaker with Secondary Fixation Capability
US20110017610A1 (en) * 2007-09-03 2011-01-27 Alexander Hahn Device and process for breaking down pollutants in a liquid and also use of such a device
US20110077708A1 (en) * 2009-09-28 2011-03-31 Alan Ostroff MRI Compatible Leadless Cardiac Pacemaker
US20110152968A1 (en) * 2005-11-16 2011-06-23 Bioness Neuromodulation Ltd. Orthosis for a gait modulation system
US8080064B2 (en) 2007-06-29 2011-12-20 Depuy Products, Inc. Tibial tray assembly having a wireless communication device
US8209022B2 (en) 2005-11-16 2012-06-26 Bioness Neuromodulation Ltd. Gait modulation system and method
US8489196B2 (en) 2003-10-03 2013-07-16 Medtronic, Inc. System, apparatus and method for interacting with a targeted tissue of a patient
US8543205B2 (en) 2010-10-12 2013-09-24 Nanostim, Inc. Temperature sensor for a leadless cardiac pacemaker
US8615310B2 (en) 2010-12-13 2013-12-24 Pacesetter, Inc. Delivery catheter systems and methods
US8712522B1 (en) * 2005-10-18 2014-04-29 Cvrx, Inc. System for setting programmable parameters for an implantable hypertension treatment device
US8972017B2 (en) 2005-11-16 2015-03-03 Bioness Neuromodulation Ltd. Gait modulation system and method
US9020611B2 (en) 2010-10-13 2015-04-28 Pacesetter, Inc. Leadless cardiac pacemaker with anti-unscrewing feature
US9060692B2 (en) 2010-10-12 2015-06-23 Pacesetter, Inc. Temperature sensor for a leadless cardiac pacemaker
US9126032B2 (en) 2010-12-13 2015-09-08 Pacesetter, Inc. Pacemaker retrieval systems and methods
US9168383B2 (en) 2005-10-14 2015-10-27 Pacesetter, Inc. Leadless cardiac pacemaker with conducted communication
US9242102B2 (en) 2010-12-20 2016-01-26 Pacesetter, Inc. Leadless pacemaker with radial fixation mechanism
US9511236B2 (en) 2011-11-04 2016-12-06 Pacesetter, Inc. Leadless cardiac pacemaker with integral battery and redundant welds
US9802054B2 (en) 2012-08-01 2017-10-31 Pacesetter, Inc. Biostimulator circuit with flying cell
US9867985B2 (en) 2014-03-24 2018-01-16 Bioness Inc. Systems and apparatus for gait modulation and methods of use
US11045654B2 (en) 2017-11-29 2021-06-29 Medtronic, Inc. Tissue conduction communication using ramped drive signal
US11077300B2 (en) 2016-01-11 2021-08-03 Bioness Inc. Systems and apparatus for gait modulation and methods of use
US11110279B2 (en) 2017-11-29 2021-09-07 Medtronic, Inc. Signal transmission optimization for tissue conduction communication
US11213684B2 (en) 2017-11-29 2022-01-04 Medtronic, Inc. Device and method to reduce artifact from tissue conduction communication transmission
US11229796B2 (en) 2017-12-15 2022-01-25 Medtronic Inc. Device, system and method with adaptive timing for tissue conduction communication transmission
US11235162B2 (en) 2017-11-29 2022-02-01 Medtronic, Inc. Tissue conduction communication between devices

Families Citing this family (528)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US8684009B2 (en) * 1997-02-26 2014-04-01 Alfred E. Mann Foundation For Scientific Research System for determining relative distance(s) and/or angle(s) between at least two points
US7114502B2 (en) * 1997-02-26 2006-10-03 Alfred E. Mann Foundation For Scientific Research Battery-powered patient implantable device
US6695885B2 (en) 1997-02-26 2004-02-24 Alfred E. Mann Foundation For Scientific Research Method and apparatus for coupling an implantable stimulator/sensor to a prosthetic device
US7107103B2 (en) * 1997-02-26 2006-09-12 Alfred E. Mann Foundation For Scientific Research Full-body charger for battery-powered patient implantable device
US8555894B2 (en) * 1997-02-26 2013-10-15 Alfred E. Mann Foundation For Scientific Research System for monitoring temperature
US6164284A (en) * 1997-02-26 2000-12-26 Schulman; Joseph H. System of implantable devices for monitoring and/or affecting body parameters
US6208894B1 (en) * 1997-02-26 2001-03-27 Alfred E. Mann Foundation For Scientific Research And Advanced Bionics System of implantable devices for monitoring and/or affecting body parameters
US20030036746A1 (en) 2001-08-16 2003-02-20 Avi Penner Devices for intrabody delivery of molecules and systems and methods utilizing same
US8480580B2 (en) 1998-04-30 2013-07-09 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US8974386B2 (en) 1998-04-30 2015-03-10 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US8346337B2 (en) 1998-04-30 2013-01-01 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US6949816B2 (en) 2003-04-21 2005-09-27 Motorola, Inc. Semiconductor component having first surface area for electrically coupling to a semiconductor chip and second surface area for electrically coupling to a substrate, and method of manufacturing same
US9066695B2 (en) 1998-04-30 2015-06-30 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US8688188B2 (en) 1998-04-30 2014-04-01 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US6175752B1 (en) 1998-04-30 2001-01-16 Therasense, Inc. Analyte monitoring device and methods of use
US8465425B2 (en) 1998-04-30 2013-06-18 Abbott Diabetes Care Inc. Analyte monitoring device and methods of use
US7890176B2 (en) 1998-07-06 2011-02-15 Boston Scientific Neuromodulation Corporation Methods and systems for treating chronic pelvic pain
ATE394662T1 (en) * 1998-08-26 2008-05-15 Sensors For Med & Science Inc OPTICALLY BASED SENSOR DEVICES
US20020041987A1 (en) * 1998-10-23 2002-04-11 Joseph H. Schulman Prismatic zincair battery for use with biological stimulator
WO2000038783A1 (en) * 1998-12-31 2000-07-06 Ball Semiconductor, Inc. Injectable thermal balls for tumor ablation
US6654642B2 (en) * 1999-09-29 2003-11-25 Medtronic, Inc. Patient interactive neurostimulation system and method
US7478108B2 (en) * 1999-12-06 2009-01-13 Micro Strain, Inc. Data collection using sensing units and separate control units with all power derived from the control units
US6582441B1 (en) 2000-02-24 2003-06-24 Advanced Bionics Corporation Surgical insertion tool
US6958677B1 (en) * 2000-03-31 2005-10-25 Ge Medical Systems Information Technologies, Inc. Object location monitoring system
US6650943B1 (en) 2000-04-07 2003-11-18 Advanced Bionics Corporation Fully implantable neurostimulator for cavernous nerve stimulation as a therapy for erectile dysfunction and other sexual dysfunction
AU2001263022A1 (en) * 2000-05-12 2001-11-26 Therasense, Inc. Electrodes with multilayer membranes and methods of using and making the electrodes
US8914114B2 (en) 2000-05-23 2014-12-16 The Feinstein Institute For Medical Research Inhibition of inflammatory cytokine production by cholinergic agonists and vagus nerve stimulation
US7553280B2 (en) * 2000-06-29 2009-06-30 Sensors For Medicine And Science, Inc. Implanted sensor processing system and method
DE60143621D1 (en) 2000-09-13 2011-01-20 DEVICE FOR CONDITIONING MUSCLES IN SLEEP
DE60142178D1 (en) * 2000-10-11 2010-07-01 Mann Alfred E Found Scient Res IMPROVED ANTENNA FOR AN IMPLANTED MEDICAL MINIATURE DEVICE
US7283874B2 (en) 2000-10-16 2007-10-16 Remon Medical Technologies Ltd. Acoustically powered implantable stimulating device
US7198603B2 (en) * 2003-04-14 2007-04-03 Remon Medical Technologies, Inc. Apparatus and methods using acoustic telemetry for intrabody communications
US7024248B2 (en) 2000-10-16 2006-04-04 Remon Medical Technologies Ltd Systems and methods for communicating with implantable devices
US6764446B2 (en) * 2000-10-16 2004-07-20 Remon Medical Technologies Ltd Implantable pressure sensors and methods for making and using them
US6560471B1 (en) 2001-01-02 2003-05-06 Therasense, Inc. Analyte monitoring device and methods of use
US6445953B1 (en) * 2001-01-16 2002-09-03 Kenergy, Inc. Wireless cardiac pacing system with vascular electrode-stents
US7493172B2 (en) * 2001-01-30 2009-02-17 Boston Scientific Neuromodulation Corp. Methods and systems for stimulating a nerve originating in an upper cervical spine area to treat a medical condition
US20050143789A1 (en) * 2001-01-30 2005-06-30 Whitehurst Todd K. Methods and systems for stimulating a peripheral nerve to treat chronic pain
US20060064140A1 (en) * 2001-01-30 2006-03-23 Whitehurst Todd K Methods and systems for stimulating a trigeminal nerve to treat a psychiatric disorder
US6753783B2 (en) * 2001-03-30 2004-06-22 Augmentech, Inc. Patient positioning monitoring apparatus and method of use thereof
US6885895B1 (en) 2001-04-26 2005-04-26 Advanced Bionics Corporation Methods and systems for electrical and/or drug stimulation as a therapy for erectile dysfunction
US6551345B2 (en) * 2001-04-26 2003-04-22 Alfred E. Mann Foundation For Scientific Research Protection apparatus for implantable medical device
US6901296B1 (en) 2001-05-25 2005-05-31 Advanced Bionics Corporation Methods and systems for direct electrical current stimulation as a therapy for cancer and other neoplastic diseases
US6901294B1 (en) 2001-05-25 2005-05-31 Advanced Bionics Corporation Methods and systems for direct electrical current stimulation as a therapy for prostatic hypertrophy
US20030204218A1 (en) * 2001-04-26 2003-10-30 Vogel Martin J. Protection apparatus for implantable medical device
BR0209357A (en) * 2001-05-04 2004-06-08 Sensors For Med & Science Inc Electro-reading device with reference channel
US6733485B1 (en) 2001-05-25 2004-05-11 Advanced Bionics Corporation Microstimulator-based electrochemotherapy methods and systems
US6472991B1 (en) 2001-06-15 2002-10-29 Alfred E. Mann Foundation For Scientific Research Multichannel communication protocol configured to extend the battery life of an implantable device
US6792314B2 (en) * 2001-06-18 2004-09-14 Alfred E. Mann Foundation For Scientific Research Miniature implantable array and stimulation system suitable for eyelid stimulation
DE60235473D1 (en) 2001-06-18 2010-04-08 Mann Alfred E Found Scient Res Implantable miniature connectors
US6947782B2 (en) * 2001-06-18 2005-09-20 Alfred E. Mann Foundation For Scientific Research Miniature implantable connectors
US7054692B1 (en) 2001-06-22 2006-05-30 Advanced Bionics Corporation Fixation device for implantable microdevices
US7727221B2 (en) * 2001-06-27 2010-06-01 Cardiac Pacemakers Inc. Method and device for electrochemical formation of therapeutic species in vivo
US6786860B2 (en) 2001-10-03 2004-09-07 Advanced Bionics Corporation Hearing aid design
US7127078B2 (en) * 2001-10-03 2006-10-24 Advanced Bionics Corporation Implanted outer ear canal hearing aid
US6879695B2 (en) * 2001-10-03 2005-04-12 Advanced Bionics Corporation Personal sound link module
WO2003033070A1 (en) * 2001-10-16 2003-04-24 Case Western Reserve University Neural prosthesis
US6894456B2 (en) * 2001-11-07 2005-05-17 Quallion Llc Implantable medical power module
WO2003063242A1 (en) * 2002-01-16 2003-07-31 Alfred E. Mann Foundation For Scientific Research Space-saving packaging of electronic circuits
AUPS006902A0 (en) * 2002-01-21 2002-02-07 Neopraxis Pty Ltd A multi-purpose fes system
US7231252B2 (en) * 2002-01-21 2007-06-12 Neopraxis Pty Ltd. FES stimulator having multiple bundled leads
US7361134B2 (en) * 2002-01-25 2008-04-22 University Of Wollongong Method and apparatus for real time dosimetry
US8364278B2 (en) * 2002-01-29 2013-01-29 Boston Scientific Neuromodulation Corporation Lead assembly for implantable microstimulator
US7024249B2 (en) * 2002-02-21 2006-04-04 Alfred E. Mann Foundation For Scientific Research Pulsed magnetic control system for interlocking functions of battery powered living tissue stimulators
US6839596B2 (en) 2002-02-21 2005-01-04 Alfred E. Mann Foundation For Scientific Research Magnet control system for battery powered living tissue stimulators
US7003356B2 (en) 2002-03-08 2006-02-21 Quallion Llc Battery terminal sealing and supporting device and method
AUPS101502A0 (en) * 2002-03-11 2002-04-11 Neopraxis Pty Ltd Wireless fes system
US7235050B2 (en) * 2002-04-11 2007-06-26 Alfred E. Mann Foundation For Scientific Research Implantable device for processing neurological signals
US6990372B2 (en) * 2002-04-11 2006-01-24 Alfred E. Mann Foundation For Scientific Research Programmable signal analysis device for detecting neurological signals in an implantable device
US7151961B1 (en) * 2002-05-24 2006-12-19 Advanced Bionics Corporation Treatment of movement disorders by brain stimulation
US7822480B2 (en) * 2002-06-28 2010-10-26 Boston Scientific Neuromodulation Corporation Systems and methods for communicating with an implantable stimulator
EP2462983A1 (en) * 2002-06-28 2012-06-13 Boston Scientific Neuromodulation Corporation Microstimulator having self-contained power source and bi-directional telemetry system
US7428438B2 (en) * 2002-06-28 2008-09-23 Boston Scientific Neuromodulation Corporation Systems and methods for providing power to a battery in an implantable stimulator
US8386048B2 (en) * 2002-06-28 2013-02-26 Boston Scientific Neuromodulation Corporation Systems and methods for communicating with or providing power to an implantable stimulator
US7254449B2 (en) * 2002-07-31 2007-08-07 Advanced Bionics Corp Systems and methods for providing power to one or more implantable devices
US20040049240A1 (en) * 2002-09-06 2004-03-11 Martin Gerber Electrical and/or magnetic stimulation therapy for the treatment of prostatitis and prostatodynia
US7727181B2 (en) * 2002-10-09 2010-06-01 Abbott Diabetes Care Inc. Fluid delivery device with autocalibration
EP1552146B1 (en) 2002-10-09 2011-04-20 Abbott Diabetes Care Inc. Fluid delivery device, system and method
US7993108B2 (en) 2002-10-09 2011-08-09 Abbott Diabetes Care Inc. Variable volume, shape memory actuated insulin dispensing pump
US6959217B2 (en) * 2002-10-24 2005-10-25 Alfred E. Mann Foundation For Scientific Research Multi-mode crystal oscillator system selectively configurable to minimize power consumption or noise generation
US7912529B2 (en) * 2002-12-30 2011-03-22 Calypso Medical Technologies, Inc. Panel-type sensor/source array assembly
US9248003B2 (en) * 2002-12-30 2016-02-02 Varian Medical Systems, Inc. Receiver used in marker localization sensing system and tunable to marker frequency
US7926491B2 (en) * 2002-12-31 2011-04-19 Calypso Medical Technologies, Inc. Method and apparatus for sensing field strength signals to estimate location of a wireless implantable marker
EP1578262A4 (en) 2002-12-31 2007-12-05 Therasense Inc Continuous glucose monitoring system and methods of use
US20040135473A1 (en) * 2003-01-15 2004-07-15 Byers Charles L. Piezoelectric devices mounted on integrated circuit chip
US7548786B2 (en) * 2003-04-02 2009-06-16 Medtronic, Inc. Library for management of neurostimulation therapy programs
US7894908B2 (en) * 2003-04-02 2011-02-22 Medtronic, Inc. Neurostimulation therapy optimization based on a rated session log
US7505815B2 (en) * 2003-04-02 2009-03-17 Medtronic, Inc. Neurostimulation therapy usage diagnostics
US7489970B2 (en) * 2003-04-02 2009-02-10 Medtronic, Inc. Management of neurostimulation therapy using parameter sets
US7302294B2 (en) * 2003-04-11 2007-11-27 Cardiac Pacemakers, Inc. Subcutaneous cardiac sensing and stimulation system employing blood sensor
SG182002A1 (en) * 2003-04-15 2012-07-30 Sensors For Med & Science Inc System and method for attenuating the effect of ambient light on an optical sensor
US7679407B2 (en) 2003-04-28 2010-03-16 Abbott Diabetes Care Inc. Method and apparatus for providing peak detection circuitry for data communication systems
US20070083240A1 (en) * 2003-05-08 2007-04-12 Peterson David K L Methods and systems for applying stimulation and sensing one or more indicators of cardiac activity with an implantable stimulator
US20070021804A1 (en) * 2003-05-30 2007-01-25 Maltan Albert A Stimulation using a microstimulator to treat tinnitus
WO2005000398A2 (en) * 2003-06-04 2005-01-06 Synecor Intravascular electrophysiological system and methods
US7617007B2 (en) * 2003-06-04 2009-11-10 Synecor Llc Method and apparatus for retaining medical implants within body vessels
US8239045B2 (en) 2003-06-04 2012-08-07 Synecor Llc Device and method for retaining a medical device within a vessel
US7082336B2 (en) * 2003-06-04 2006-07-25 Synecor, Llc Implantable intravascular device for defibrillation and/or pacing
US8066639B2 (en) 2003-06-10 2011-11-29 Abbott Diabetes Care Inc. Glucose measuring device for use in personal area network
US7239921B2 (en) * 2003-06-23 2007-07-03 Alfred E. Mann Foundation For Scientific Research Housing for an implantable medical device
US7252005B2 (en) 2003-08-22 2007-08-07 Alfred E. Mann Foundation For Scientific Research System and apparatus for sensing pressure in living organisms and inanimate objects
EP1508302A3 (en) 2003-08-22 2005-04-20 Alfred E. Mann Foundation for Scientific Research A system for determining relative distance(s) and/or angle(s) between at least two points
EP1508299B1 (en) * 2003-08-22 2013-04-03 Alfred E. Mann Foundation for Scientific Research An implantable device for processing neurological signals
US8086323B2 (en) * 2003-09-23 2011-12-27 Medtronic Minimed, Inc. Implantable multi-parameter sensing system and method
US6821154B1 (en) 2003-10-03 2004-11-23 Alfred E. Mann Foundation For Scientific Research Electrical device connector and method therefor
US6935897B2 (en) * 2003-10-03 2005-08-30 Alfred E. Mann Foundation For Scientific Research Electrical device connector and method therefor
US20050085874A1 (en) * 2003-10-17 2005-04-21 Ross Davis Method and system for treating sleep apnea
US7379774B2 (en) * 2003-10-17 2008-05-27 Alfred E. Mann Foundation For Scientific Research Method and apparatus for efficient power/data transmission
ATE482650T1 (en) * 2003-11-03 2010-10-15 Microchips Inc MEDICAL DEVICE FOR MEASURING GLUCOSE
US7657312B2 (en) 2003-11-03 2010-02-02 Cardiac Pacemakers, Inc. Multi-site ventricular pacing therapy with parasympathetic stimulation
US20060074449A1 (en) * 2003-11-03 2006-04-06 Stephen Denker Intravascular stimulation system with wireless power supply
US7450998B2 (en) 2003-11-21 2008-11-11 Alfred E. Mann Foundation For Scientific Research Method of placing an implantable device proximate to neural/muscular tissue
EP1701766A2 (en) * 2003-12-12 2006-09-20 Synecor, LLC Implantable medical device having pre-implant exoskeleton
US20050137652A1 (en) * 2003-12-19 2005-06-23 The Board of Regents of the University of Texas at Dallas System and method for interfacing cellular matter with a machine
US20090198293A1 (en) * 2003-12-19 2009-08-06 Lawrence Cauller Microtransponder Array for Implant
WO2005062829A2 (en) * 2003-12-19 2005-07-14 Advanced Bionics Corporation Skull-mounted electrical stimulation system and method for treating patients
US7643875B2 (en) 2003-12-24 2010-01-05 Cardiac Pacemakers, Inc. Baroreflex stimulation system to reduce hypertension
US8024050B2 (en) 2003-12-24 2011-09-20 Cardiac Pacemakers, Inc. Lead for stimulating the baroreceptors in the pulmonary artery
US20050149133A1 (en) * 2003-12-24 2005-07-07 Imad Libbus Sensing with compensation for neural stimulator
US8396560B2 (en) 2004-11-18 2013-03-12 Cardiac Pacemakers, Inc. System and method for closed-loop neural stimulation
US8126560B2 (en) 2003-12-24 2012-02-28 Cardiac Pacemakers, Inc. Stimulation lead for stimulating the baroreceptors in the pulmonary artery
US7869881B2 (en) 2003-12-24 2011-01-11 Cardiac Pacemakers, Inc. Baroreflex stimulator with integrated pressure sensor
US7769450B2 (en) 2004-11-18 2010-08-03 Cardiac Pacemakers, Inc. Cardiac rhythm management device with neural sensor
US20050149132A1 (en) 2003-12-24 2005-07-07 Imad Libbus Automatic baroreflex modulation based on cardiac activity
US20050154284A1 (en) * 2003-12-31 2005-07-14 Wright J. N. Method and system for calibration of a marker localization sensing array
US7026927B2 (en) * 2003-12-31 2006-04-11 Calypso Medical Technologies, Inc. Receiver used in marker localization sensing system and having dithering in excitation pulses
US7684849B2 (en) * 2003-12-31 2010-03-23 Calypso Medical Technologies, Inc. Marker localization sensing system synchronized with radiation source
US20050154280A1 (en) * 2003-12-31 2005-07-14 Wright J. N. Receiver used in marker localization sensing system
US7979137B2 (en) * 2004-02-11 2011-07-12 Ethicon, Inc. System and method for nerve stimulation
US8751003B2 (en) 2004-02-11 2014-06-10 Ethicon, Inc. Conductive mesh for neurostimulation
US8165695B2 (en) 2004-02-11 2012-04-24 Ethicon, Inc. System and method for selectively stimulating different body parts
US7647112B2 (en) * 2004-02-11 2010-01-12 Ethicon, Inc. System and method for selectively stimulating different body parts
AU2005212165A1 (en) * 2004-02-11 2005-08-25 Ethicon, Inc. System and method for urodynamic evaluation utilizing micro-electronic mechanical system
WO2005089103A2 (en) 2004-02-17 2005-09-29 Therasense, Inc. Method and system for providing data communication in continuous glucose monitoring and management system
US8057401B2 (en) 2005-02-24 2011-11-15 Erich Wolf System for transcutaneous monitoring of intracranial pressure
US7435229B2 (en) * 2004-02-25 2008-10-14 Wolf Erich W System for transcutaneous monitoring of intracranial pressure (ICP) using near infrared (NIR) telemetry
US7406105B2 (en) * 2004-03-03 2008-07-29 Alfred E. Mann Foundation For Scientific Research System and method for sharing a common communication channel between multiple systems of implantable medical devices
US10912712B2 (en) 2004-03-25 2021-02-09 The Feinstein Institutes For Medical Research Treatment of bleeding by non-invasive stimulation
US7857767B2 (en) 2004-04-19 2010-12-28 Invention Science Fund I, Llc Lumen-traveling device
US8092549B2 (en) 2004-09-24 2012-01-10 The Invention Science Fund I, Llc Ciliated stent-like-system
US8353896B2 (en) 2004-04-19 2013-01-15 The Invention Science Fund I, Llc Controllable release nasal system
US7998060B2 (en) 2004-04-19 2011-08-16 The Invention Science Fund I, Llc Lumen-traveling delivery device
US8024036B2 (en) 2007-03-19 2011-09-20 The Invention Science Fund I, Llc Lumen-traveling biological interface device and method of use
US8337482B2 (en) 2004-04-19 2012-12-25 The Invention Science Fund I, Llc System for perfusion management
US7850676B2 (en) 2004-04-19 2010-12-14 The Invention Science Fund I, Llc System with a reservoir for perfusion management
US8512219B2 (en) 2004-04-19 2013-08-20 The Invention Science Fund I, Llc Bioelectromagnetic interface system
US8361013B2 (en) 2004-04-19 2013-01-29 The Invention Science Fund I, Llc Telescoping perfusion management system
US9011329B2 (en) 2004-04-19 2015-04-21 Searete Llc Lumenally-active device
US7245972B2 (en) * 2004-04-29 2007-07-17 Alfred E. Mann Foundation For Scientific Research Electrical treatment to treat shoulder subluxation
US20050267555A1 (en) 2004-05-28 2005-12-01 Marnfeldt Goran N Engagement tool for implantable medical devices
JP2008501037A (en) * 2004-06-01 2008-01-17 マイクロチップス・インコーポレーテッド Devices and methods for measuring and enhancing transport of drugs or analytes to / from medical implants
US7761167B2 (en) * 2004-06-10 2010-07-20 Medtronic Urinary Solutions, Inc. Systems and methods for clinician control of stimulation systems
US20080027513A1 (en) * 2004-07-09 2008-01-31 Advanced Bionics Corporation Systems And Methods For Using A Butterfly Coil To Communicate With Or Transfer Power To An Implantable Medical Device
CA2573785A1 (en) * 2004-07-20 2006-02-02 Medtronic, Inc. Therapy programming guidance based on stored programming history
US7819909B2 (en) * 2004-07-20 2010-10-26 Medtronic, Inc. Therapy programming guidance based on stored programming history
US8452407B2 (en) * 2004-08-16 2013-05-28 Boston Scientific Neuromodulation Corporation Methods for treating gastrointestinal disorders
US20060064142A1 (en) 2004-09-17 2006-03-23 Cardiac Pacemakers, Inc. Systems and methods for deriving relative physiologic measurements using an implanted sensor device
US8560041B2 (en) 2004-10-04 2013-10-15 Braingate Co., Llc Biological interface system
US7771838B1 (en) 2004-10-12 2010-08-10 Boston Scientific Neuromodulation Corporation Hermetically bonding ceramic and titanium with a Ti-Pd braze interface
US8329314B1 (en) 2004-10-12 2012-12-11 Boston Scientific Neuromodulation Corporation Hermetically bonding ceramic and titanium with a palladium braze
US7647109B2 (en) 2004-10-20 2010-01-12 Boston Scientific Scimed, Inc. Leadless cardiac stimulation systems
US7532933B2 (en) 2004-10-20 2009-05-12 Boston Scientific Scimed, Inc. Leadless cardiac stimulation systems
CA2583404A1 (en) 2004-10-20 2006-04-27 Boston Scientific Limited Leadless cardiac stimulation systems
US8489189B2 (en) * 2004-10-29 2013-07-16 Medtronic, Inc. Expandable fixation mechanism
US20060095077A1 (en) * 2004-10-29 2006-05-04 Tronnes Carole A Expandable fixation structures
US9358393B1 (en) 2004-11-09 2016-06-07 Andres M. Lozano Stimulation methods and systems for treating an auditory dysfunction
US8332047B2 (en) 2004-11-18 2012-12-11 Cardiac Pacemakers, Inc. System and method for closed-loop neural stimulation
US7813808B1 (en) 2004-11-24 2010-10-12 Remon Medical Technologies Ltd Implanted sensor system with optimized operational and sensing parameters
US7237712B2 (en) 2004-12-01 2007-07-03 Alfred E. Mann Foundation For Scientific Research Implantable device and communication integrated circuit implementable therein
US7542804B2 (en) 2004-12-03 2009-06-02 Alfred E. Mann Foundation For Scientific Research Neuromuscular stimulation to avoid pulmonary embolisms
US20060122661A1 (en) * 2004-12-03 2006-06-08 Mandell Lee J Diaphragmatic pacing with activity monitor adjustment
US7483746B2 (en) * 2004-12-06 2009-01-27 Boston Scientific Neuromodulation Corp. Stimulation of the stomach in response to sensed parameters to treat obesity
US8818504B2 (en) 2004-12-16 2014-08-26 Cardiac Pacemakers Inc Leadless cardiac stimulation device employing distributed logic
US20060161217A1 (en) * 2004-12-21 2006-07-20 Jaax Kristen N Methods and systems for treating obesity
US9095713B2 (en) * 2004-12-21 2015-08-04 Allison M. Foster Methods and systems for treating autism by decreasing neural activity within the brain
US20070038264A1 (en) * 2004-12-21 2007-02-15 Jaax Kristen N Methods and systems for treating autism
US9327069B2 (en) 2004-12-21 2016-05-03 Boston Scientific Neuromodulation Corporation Methods and systems for treating a medical condition by promoting neural remodeling within the brain
US9352145B2 (en) * 2004-12-22 2016-05-31 Boston Scientific Neuromodulation Corporation Methods and systems for treating a psychotic disorder
US8515541B1 (en) 2004-12-22 2013-08-20 Boston Scientific Neuromodulation Corporation Methods and systems for treating post-stroke disorders
US11207518B2 (en) 2004-12-27 2021-12-28 The Feinstein Institutes For Medical Research Treating inflammatory disorders by stimulation of the cholinergic anti-inflammatory pathway
AU2005323463B2 (en) * 2004-12-27 2009-11-19 The Feinstein Institutes For Medical Research Treating inflammatory disorders by electrical vagus nerve stimulation
US7901368B2 (en) 2005-01-06 2011-03-08 Braingate Co., Llc Neurally controlled patient ambulation system
US8095209B2 (en) 2005-01-06 2012-01-10 Braingate Co., Llc Biological interface system with gated control signal
WO2006081279A2 (en) * 2005-01-25 2006-08-03 Microchips, Inc. Control of drug release by transient modification of local microenvironments
US7376466B2 (en) * 2005-01-26 2008-05-20 Boston Scientific Neuromodulation Corporation Casings for implantable stimulators and methods of making the same
US7294108B1 (en) * 2005-01-27 2007-11-13 Pacesetter, Inc. Cardiac event microrecorder and method for implanting same
US20060293578A1 (en) * 2005-02-03 2006-12-28 Rennaker Robert L Ii Brian machine interface device
US7657316B2 (en) * 2005-02-25 2010-02-02 Boston Scientific Neuromodulation Corporation Methods and systems for stimulating a motor cortex of the brain to treat a medical condition
US8165696B2 (en) * 2005-02-25 2012-04-24 Boston Scientific Neuromodulation Corporation Multiple-pronged implantable stimulator and methods of making and using such a stimulator
US20060194724A1 (en) * 2005-02-25 2006-08-31 Whitehurst Todd K Methods and systems for nerve regeneration
US20060200205A1 (en) * 2005-03-01 2006-09-07 Haller Matthew I Systems and methods for treating a patient with multiple stimulation therapies
US7853321B2 (en) * 2005-03-14 2010-12-14 Boston Scientific Neuromodulation Corporation Stimulation of a stimulation site within the neck or head
US7920915B2 (en) * 2005-11-16 2011-04-05 Boston Scientific Neuromodulation Corporation Implantable stimulator
US7848803B1 (en) 2005-03-14 2010-12-07 Boston Scientific Neuromodulation Corporation Methods and systems for facilitating stimulation of one or more stimulation sites
US8423155B1 (en) 2005-03-14 2013-04-16 Boston Scientific Neuromodulation Corporation Methods and systems for facilitating stimulation of one or more stimulation sites
US20060202805A1 (en) * 2005-03-14 2006-09-14 Alfred E. Mann Foundation For Scientific Research Wireless acquisition and monitoring system
US7627383B2 (en) * 2005-03-15 2009-12-01 Boston Scientific Neuromodulation Corporation Implantable stimulator
EP1863559A4 (en) 2005-03-21 2008-07-30 Abbott Diabetes Care Inc Method and system for providing integrated medication infusion and analyte monitoring system
US7660628B2 (en) 2005-03-23 2010-02-09 Cardiac Pacemakers, Inc. System to provide myocardial and neural stimulation
US7499748B2 (en) * 2005-04-11 2009-03-03 Cardiac Pacemakers, Inc. Transvascular neural stimulation device
US7308292B2 (en) 2005-04-15 2007-12-11 Sensors For Medicine And Science, Inc. Optical-based sensing devices
US8112240B2 (en) 2005-04-29 2012-02-07 Abbott Diabetes Care Inc. Method and apparatus for providing leak detection in data monitoring and management systems
DE102005021412A1 (en) * 2005-05-04 2006-11-09 Otto Bock Healthcare Products Gmbh System of a liner with a myoelectric electrode unit
US7617003B2 (en) * 2005-05-16 2009-11-10 Cardiac Pacemakers, Inc. System for selective activation of a nerve trunk using a transvascular reshaping lead
US7200504B1 (en) 2005-05-16 2007-04-03 Advanced Bionics Corporation Measuring temperature change in an electronic biomedical implant
US7768408B2 (en) 2005-05-17 2010-08-03 Abbott Diabetes Care Inc. Method and system for providing data management in data monitoring system
US8391990B2 (en) 2005-05-18 2013-03-05 Cardiac Pacemakers, Inc. Modular antitachyarrhythmia therapy system
US7801600B1 (en) 2005-05-26 2010-09-21 Boston Scientific Neuromodulation Corporation Controlling charge flow in the electrical stimulation of tissue
EP1887925A2 (en) * 2005-05-27 2008-02-20 The Cleveland Clinic Foundation Method and apparatus for eddy current compensation in a radio frequency probe
US7447549B2 (en) * 2005-06-01 2008-11-04 Advanced Bionioics, Llc Methods and systems for denoising a neural recording signal
US7343200B2 (en) * 2005-06-01 2008-03-11 Advanced Bionics, Llc Methods and systems for automatically determining a neural response threshold current level
US7818052B2 (en) * 2005-06-01 2010-10-19 Advanced Bionics, Llc Methods and systems for automatically identifying whether a neural recording signal includes a neural response signal
US7620437B2 (en) 2005-06-03 2009-11-17 Abbott Diabetes Care Inc. Method and apparatus for providing rechargeable power in data monitoring and management systems
US8588930B2 (en) * 2005-06-07 2013-11-19 Ethicon, Inc. Piezoelectric stimulation device
US7857766B2 (en) * 2005-06-20 2010-12-28 Alfred E. Mann Foundation For Scientific Research System of implantable ultrasonic emitters for preventing restenosis following a stent procedure
US7563279B2 (en) * 2005-06-20 2009-07-21 Alfred E. Mann Foundation For Scientific Research Stent having an ultrasonic emitter
EP1906815A2 (en) * 2005-07-12 2008-04-09 Alfred E. Mann Institute for Biomedical Engineering at the University of Southern California Method and apparatus for detecting object orientation and position
US8175717B2 (en) * 2005-09-06 2012-05-08 Boston Scientific Neuromodulation Corporation Ultracapacitor powered implantable pulse generator with dedicated power supply
US7684858B2 (en) * 2005-09-21 2010-03-23 Boston Scientific Neuromodulation Corporation Methods and systems for placing an implanted stimulator for stimulating tissue
US7756561B2 (en) 2005-09-30 2010-07-13 Abbott Diabetes Care Inc. Method and apparatus for providing rechargeable power in data monitoring and management systems
US7616990B2 (en) 2005-10-24 2009-11-10 Cardiac Pacemakers, Inc. Implantable and rechargeable neural stimulator
US7583190B2 (en) 2005-10-31 2009-09-01 Abbott Diabetes Care Inc. Method and apparatus for providing data communication in data monitoring and management systems
US7684867B2 (en) * 2005-11-01 2010-03-23 Boston Scientific Neuromodulation Corporation Treatment of aphasia by electrical stimulation and/or drug infusion
US7872884B2 (en) * 2005-11-03 2011-01-18 Boston Scientific Neuromodulation Corporation Cascaded step-up converter and charge pump for efficient compliance voltage generation in an implantable stimulator device
US7766829B2 (en) 2005-11-04 2010-08-03 Abbott Diabetes Care Inc. Method and system for providing basal profile modification in analyte monitoring and management systems
US7595723B2 (en) 2005-11-14 2009-09-29 Edwards Lifesciences Corporation Wireless communication protocol for a medical sensor system
US7729758B2 (en) 2005-11-30 2010-06-01 Boston Scientific Neuromodulation Corporation Magnetically coupled microstimulators
WO2007067231A1 (en) 2005-12-09 2007-06-14 Boston Scientific Scimed, Inc. Cardiac stimulation system
US8050774B2 (en) 2005-12-22 2011-11-01 Boston Scientific Scimed, Inc. Electrode apparatus, systems and methods
US20100023021A1 (en) * 2005-12-27 2010-01-28 Flaherty J Christopher Biological Interface and Insertion
US7610100B2 (en) * 2005-12-30 2009-10-27 Boston Scientific Neuromodulation Corporation Methods and systems for treating osteoarthritis
US8840660B2 (en) 2006-01-05 2014-09-23 Boston Scientific Scimed, Inc. Bioerodible endoprostheses and methods of making the same
US8078278B2 (en) 2006-01-10 2011-12-13 Remon Medical Technologies Ltd. Body attachable unit in wireless communication with implantable devices
WO2007087875A1 (en) * 2006-01-13 2007-08-09 Universität Duisburg-Essen Stimulation system, in particular a cardiac pacemaker
US7835803B1 (en) 2006-01-17 2010-11-16 Boston Scientific Neuromodulation Corporation Lead assemblies with one or more switching networks
US8344966B2 (en) 2006-01-31 2013-01-01 Abbott Diabetes Care Inc. Method and system for providing a fault tolerant display unit in an electronic device
US8089029B2 (en) 2006-02-01 2012-01-03 Boston Scientific Scimed, Inc. Bioabsorbable metal medical device and method of manufacture
US8175710B2 (en) * 2006-03-14 2012-05-08 Boston Scientific Neuromodulation Corporation Stimulator system with electrode array and the method of making the same
US7777641B2 (en) * 2006-03-29 2010-08-17 Advanced Bionics, Llc Systems and methods of facilitating communication between a first and second device
US7620438B2 (en) 2006-03-31 2009-11-17 Abbott Diabetes Care Inc. Method and system for powering an electronic device
US8226891B2 (en) 2006-03-31 2012-07-24 Abbott Diabetes Care Inc. Analyte monitoring devices and methods therefor
US9198563B2 (en) 2006-04-12 2015-12-01 The Invention Science Fund I, Llc Temporal control of a lumen traveling device in a body tube tree
US8048150B2 (en) 2006-04-12 2011-11-01 Boston Scientific Scimed, Inc. Endoprosthesis having a fiber meshwork disposed thereon
US20080058785A1 (en) 2006-04-12 2008-03-06 Searete Llc, A Limited Liability Corporation Of The State Of Delaware Autofluorescent imaging and target ablation
US7650185B2 (en) 2006-04-25 2010-01-19 Cardiac Pacemakers, Inc. System and method for walking an implantable medical device from a sleep state
US7908014B2 (en) * 2006-05-05 2011-03-15 Alfred E. Mann Foundation For Scientific Research Antenna on ceramic case
US7498516B1 (en) * 2006-06-14 2009-03-03 Boston Scientific Neuromodulation Corporation Feedthru assembly
US8401654B1 (en) 2006-06-30 2013-03-19 Boston Scientific Neuromodulation Corporation Methods and systems for treating one or more effects of deafferentation
US8170668B2 (en) 2006-07-14 2012-05-01 Cardiac Pacemakers, Inc. Baroreflex sensitivity monitoring and trending for tachyarrhythmia detection and therapy
US7840281B2 (en) 2006-07-21 2010-11-23 Boston Scientific Scimed, Inc. Delivery of cardiac stimulation devices
US8290600B2 (en) 2006-07-21 2012-10-16 Boston Scientific Scimed, Inc. Electrical stimulation of body tissue using interconnected electrode assemblies
US7908334B2 (en) * 2006-07-21 2011-03-15 Cardiac Pacemakers, Inc. System and method for addressing implantable devices
US7955268B2 (en) 2006-07-21 2011-06-07 Cardiac Pacemakers, Inc. Multiple sensor deployment
CA2659761A1 (en) 2006-08-02 2008-02-07 Boston Scientific Scimed, Inc. Endoprosthesis with three-dimensional disintegration control
US8457734B2 (en) 2006-08-29 2013-06-04 Cardiac Pacemakers, Inc. System and method for neural stimulation
US8644934B2 (en) 2006-09-13 2014-02-04 Boston Scientific Scimed Inc. Cardiac stimulation using leadless electrode assemblies
ES2368125T3 (en) 2006-09-15 2011-11-14 Boston Scientific Scimed, Inc. BIOEROSIONABLE ENDOPROOTHESIS WITH BIOESTABLE INORGANIC LAYERS.
CA2663271A1 (en) 2006-09-15 2008-03-20 Boston Scientific Limited Bioerodible endoprostheses and methods of making the same
US8808726B2 (en) 2006-09-15 2014-08-19 Boston Scientific Scimed. Inc. Bioerodible endoprostheses and methods of making the same
EP2959925B1 (en) 2006-09-15 2018-08-29 Boston Scientific Limited Medical devices and methods of making the same
WO2008036548A2 (en) 2006-09-18 2008-03-27 Boston Scientific Limited Endoprostheses
US7445528B1 (en) 2006-09-29 2008-11-04 Boston Scientific Neuromodulation Corporation Connector assemblies
US7818061B1 (en) 2006-10-13 2010-10-19 Advanced Bionics, Llc Systems and methods for detecting an error associated with an implantable device
US7347746B1 (en) 2006-10-27 2008-03-25 Boston Scientific Neuromodulation Corporation Receptacle connector assembly
US8579853B2 (en) 2006-10-31 2013-11-12 Abbott Diabetes Care Inc. Infusion devices and methods
US7809437B2 (en) * 2006-11-13 2010-10-05 Advanced Bionics, Llc Methods and systems for removing accumulated charge from one or more electrodes
US20080132962A1 (en) * 2006-12-01 2008-06-05 Diubaldi Anthony System and method for affecting gatric functions
CN101563025B (en) * 2006-12-21 2013-10-30 皇家飞利浦电子股份有限公司 Electrically isolated catheter with wireless sensors
EP2277563B1 (en) 2006-12-28 2014-06-25 Boston Scientific Limited Bioerodible endoprostheses and method of making the same
US7769467B1 (en) 2007-01-31 2010-08-03 Advanced Bionics, Llc Level-dependent stimulation methods and systems
US8875714B2 (en) * 2007-02-22 2014-11-04 The Invention Science Fund I, Llc Coded-sequence activation of surgical implants
US8123686B2 (en) 2007-03-01 2012-02-28 Abbott Diabetes Care Inc. Method and apparatus for providing rolling data in communication systems
EP2139556B1 (en) 2007-03-26 2014-04-23 Remon Medical Technologies Ltd. Biased acoustic switch for implantable medical device
US7945323B2 (en) * 2007-04-13 2011-05-17 Boston Scientific Neuromodulation Corporation Treatment of obesity and/or type II diabetes by stimulation of the pituitary gland
US20080262566A1 (en) * 2007-04-23 2008-10-23 Boston Scientific Neuromodulation Corporation Methods and systems of treating medication overuse headache
WO2008137452A1 (en) * 2007-05-04 2008-11-13 Kenergy Royalty Company, Llc Implantable high efficiency digital stimulation device
US8461985B2 (en) 2007-05-08 2013-06-11 Abbott Diabetes Care Inc. Analyte monitoring system and methods
US8665091B2 (en) 2007-05-08 2014-03-04 Abbott Diabetes Care Inc. Method and device for determining elapsed sensor life
US7928850B2 (en) 2007-05-08 2011-04-19 Abbott Diabetes Care Inc. Analyte monitoring system and methods
US8456301B2 (en) 2007-05-08 2013-06-04 Abbott Diabetes Care Inc. Analyte monitoring system and methods
US20080281368A1 (en) * 2007-05-09 2008-11-13 Cherik Bulkes Implantable digital device for tissue stimulation
US7630771B2 (en) * 2007-06-25 2009-12-08 Microtransponder, Inc. Grooved electrode and wireless microtransponder system
US20090005756A1 (en) * 2007-06-29 2009-01-01 Boston Scientific Neuromodulation Corporation Methods and Systems of Treating Strabismus
US8052745B2 (en) 2007-09-13 2011-11-08 Boston Scientific Scimed, Inc. Endoprosthesis
WO2009036333A1 (en) 2007-09-14 2009-03-19 Corventis, Inc. Dynamic pairing of patients to data collection gateways
US8591430B2 (en) 2007-09-14 2013-11-26 Corventis, Inc. Adherent device for respiratory monitoring
US8460189B2 (en) 2007-09-14 2013-06-11 Corventis, Inc. Adherent cardiac monitor with advanced sensing capabilities
US8116841B2 (en) 2007-09-14 2012-02-14 Corventis, Inc. Adherent device with multiple physiological sensors
EP2200499B1 (en) 2007-09-14 2019-05-01 Medtronic Monitoring, Inc. Multi-sensor patient monitor to detect impending cardiac decompensation
US8897868B2 (en) 2007-09-14 2014-11-25 Medtronic, Inc. Medical device automatic start-up upon contact to patient tissue
US8684925B2 (en) 2007-09-14 2014-04-01 Corventis, Inc. Injectable device for physiological monitoring
US8057486B2 (en) 2007-09-18 2011-11-15 Bioness Inc. Apparatus and method for inserting implants into the body
US8352026B2 (en) 2007-10-03 2013-01-08 Ethicon, Inc. Implantable pulse generators and methods for selective nerve stimulation
US8352035B2 (en) 2007-10-31 2013-01-08 Boston Scientific Neuromodulation Corporation Connector assemblies for implantable stimulators
US20090118779A1 (en) * 2007-11-07 2009-05-07 Nader Najafi Modular System For A Wireless Implantable Device
US9089707B2 (en) 2008-07-02 2015-07-28 The Board Of Regents, The University Of Texas System Systems, methods and devices for paired plasticity
WO2009070705A2 (en) * 2007-11-26 2009-06-04 Microtransponder Inc. Transfer coil architecture
DE112008003180T5 (en) * 2007-11-26 2011-03-03 Micro-Transponder, Inc., Dallas Implantable transponder systems and methods
US8457757B2 (en) 2007-11-26 2013-06-04 Micro Transponder, Inc. Implantable transponder systems and methods
WO2009110935A1 (en) * 2007-11-26 2009-09-11 Micro Transponder Inc. Array of joined microtransponders for implantation
US8121678B2 (en) 2007-12-12 2012-02-21 Cardiac Pacemakers, Inc. Implantable medical device with hall sensor
US8600512B2 (en) 2007-12-26 2013-12-03 Boston Scientific Neuromodulation Corporation Methods and systems for treating seizures caused by brain stimulation
US8041431B2 (en) 2008-01-07 2011-10-18 Cardiac Pacemakers, Inc. System and method for in situ trimming of oscillators in a pair of implantable medical devices
US8364277B2 (en) * 2008-01-10 2013-01-29 Bioness Inc. Methods and apparatus for implanting electronic implants within the body
US8915866B2 (en) 2008-01-18 2014-12-23 Warsaw Orthopedic, Inc. Implantable sensor and associated methods
US8914112B2 (en) * 2008-01-23 2014-12-16 Boston Scienctific Neuromodulation Corporation Methods and systems of treating pancreatitis pain caused by sphincter of Oddi dysfunction
US9192409B2 (en) * 2008-01-23 2015-11-24 Boston Scientific Neuromodulation Corporation Steerable stylet handle assembly
US8060209B2 (en) * 2008-01-25 2011-11-15 Boston Scientific Neuromodulation Corporation Methods and systems of treating ischemia pain in visceral organs
US8676322B2 (en) * 2008-01-30 2014-03-18 Boston Scientific Neuromodulation Corporation Methods and systems of treating pancreatitis pain
US8301262B2 (en) * 2008-02-06 2012-10-30 Cardiac Pacemakers, Inc. Direct inductive/acoustic converter for implantable medical device
WO2009099550A1 (en) 2008-02-07 2009-08-13 Cardiac Pacemakers, Inc. Wireless tissue electrostimulation
WO2009114468A2 (en) * 2008-03-11 2009-09-17 Boston Scientific Neuromodulation Corporation Systems, apparatuses, and methods for differentiating between multiple leads implanted within a patient
WO2009114548A1 (en) 2008-03-12 2009-09-17 Corventis, Inc. Heart failure decompensation prediction based on cardiac rhythm
US9662490B2 (en) 2008-03-31 2017-05-30 The Feinstein Institute For Medical Research Methods and systems for reducing inflammation by neuromodulation and administration of an anti-inflammatory drug
US9211409B2 (en) 2008-03-31 2015-12-15 The Feinstein Institute For Medical Research Methods and systems for reducing inflammation by neuromodulation of T-cell activity
US8412317B2 (en) 2008-04-18 2013-04-02 Corventis, Inc. Method and apparatus to measure bioelectric impedance of patient tissue
US7998192B2 (en) 2008-05-09 2011-08-16 Boston Scientific Scimed, Inc. Endoprostheses
US8236046B2 (en) 2008-06-10 2012-08-07 Boston Scientific Scimed, Inc. Bioerodible endoprosthesis
US20090312650A1 (en) * 2008-06-12 2009-12-17 Cardiac Pacemakers, Inc. Implantable pressure sensor with automatic measurement and storage capabilities
US8798761B2 (en) 2008-06-27 2014-08-05 Cardiac Pacemakers, Inc. Systems and methods of monitoring the acoustic coupling of medical devices
US20100023091A1 (en) * 2008-07-24 2010-01-28 Stahmann Jeffrey E Acoustic communication of implantable device status
US7985252B2 (en) 2008-07-30 2011-07-26 Boston Scientific Scimed, Inc. Bioerodible endoprosthesis
US8494650B2 (en) * 2008-08-07 2013-07-23 Bioness, Inc. Insertion tools and methods for an electrical stimulation implant
EP2337609B1 (en) 2008-08-14 2016-08-17 Cardiac Pacemakers, Inc. Performance assessment and adaptation of an acoustic communication link
US8382824B2 (en) 2008-10-03 2013-02-26 Boston Scientific Scimed, Inc. Medical implant having NANO-crystal grains with barrier layers of metal nitrides or fluorides
US8593107B2 (en) 2008-10-27 2013-11-26 Cardiac Pacemakers, Inc. Methods and systems for recharging an implanted device by delivering a section of a charging device adjacent the implanted device within a body
US9353733B2 (en) 2008-12-04 2016-05-31 Deep Science, Llc Device and system for generation of power from intraluminal pressure changes
US9526418B2 (en) 2008-12-04 2016-12-27 Deep Science, Llc Device for storage of intraluminally generated power
US9567983B2 (en) 2008-12-04 2017-02-14 Deep Science, Llc Method for generation of power from intraluminal pressure changes
US9631610B2 (en) 2008-12-04 2017-04-25 Deep Science, Llc System for powering devices from intraluminal pressure changes
US9759202B2 (en) 2008-12-04 2017-09-12 Deep Science, Llc Method for generation of power from intraluminal pressure changes
US20100140958A1 (en) * 2008-12-04 2010-06-10 Searete Llc, A Limited Liability Corporation Of The State Of Delaware Method for powering devices from intraluminal pressure changes
US8685093B2 (en) 2009-01-23 2014-04-01 Warsaw Orthopedic, Inc. Methods and systems for diagnosing, treating, or tracking spinal disorders
US8126736B2 (en) 2009-01-23 2012-02-28 Warsaw Orthopedic, Inc. Methods and systems for diagnosing, treating, or tracking spinal disorders
US8560082B2 (en) 2009-01-30 2013-10-15 Abbott Diabetes Care Inc. Computerized determination of insulin pump therapy parameters using real time and retrospective data processing
US8267992B2 (en) 2009-03-02 2012-09-18 Boston Scientific Scimed, Inc. Self-buffering medical implants
US9095436B2 (en) * 2009-04-14 2015-08-04 The Invention Science Fund I, Llc Adjustable orthopedic implant and method for treating an orthopedic condition in a subject
US8467972B2 (en) 2009-04-28 2013-06-18 Abbott Diabetes Care Inc. Closed loop blood glucose control algorithm analysis
WO2010127050A1 (en) 2009-04-28 2010-11-04 Abbott Diabetes Care Inc. Error detection in critical repeating data in a wireless sensor system
US8788034B2 (en) 2011-05-09 2014-07-22 Setpoint Medical Corporation Single-pulse activation of the cholinergic anti-inflammatory pathway to treat chronic inflammation
US9211410B2 (en) 2009-05-01 2015-12-15 Setpoint Medical Corporation Extremely low duty-cycle activation of the cholinergic anti-inflammatory pathway to treat chronic inflammation
US8996116B2 (en) * 2009-10-30 2015-03-31 Setpoint Medical Corporation Modulation of the cholinergic anti-inflammatory pathway to treat pain or addiction
WO2010138856A1 (en) 2009-05-29 2010-12-02 Abbott Diabetes Care Inc. Medical device antenna systems having external antenna configurations
WO2010144578A2 (en) 2009-06-09 2010-12-16 Setpoint Medical Corporation Nerve cuff with pocket for leadless stimulator
ES2888427T3 (en) 2009-07-23 2022-01-04 Abbott Diabetes Care Inc Real-time management of data related to the physiological control of glucose levels
CA2771218C (en) * 2009-08-20 2015-12-29 Phillip B. Hess Optimal narrowband interference removal for signals separated in time
US9603522B2 (en) 2009-08-26 2017-03-28 Mayo Foundation For Medical Education And Research Detecting neurochemical or electrical signals within brain tissue
US8993331B2 (en) 2009-08-31 2015-03-31 Abbott Diabetes Care Inc. Analyte monitoring system and methods for managing power and noise
EP2473098A4 (en) 2009-08-31 2014-04-09 Abbott Diabetes Care Inc Analyte signal processing device and methods
US10716940B2 (en) * 2009-10-20 2020-07-21 Nyxoah SA Implant unit for modulation of small diameter nerves
WO2011050283A2 (en) 2009-10-22 2011-04-28 Corventis, Inc. Remote detection and monitoring of functional chronotropic incompetence
US9833621B2 (en) 2011-09-23 2017-12-05 Setpoint Medical Corporation Modulation of sirtuins by vagus nerve stimulation
US11051744B2 (en) 2009-11-17 2021-07-06 Setpoint Medical Corporation Closed-loop vagus nerve stimulation
US9451897B2 (en) 2009-12-14 2016-09-27 Medtronic Monitoring, Inc. Body adherent patch with electronics for physiologic monitoring
CN105126248B (en) * 2009-12-23 2018-06-12 赛博恩特医疗器械公司 For treating the nerve stimulation apparatus of chronic inflammation and system
US8668732B2 (en) 2010-03-23 2014-03-11 Boston Scientific Scimed, Inc. Surface treated bioerodible metal endoprostheses
US8965498B2 (en) 2010-04-05 2015-02-24 Corventis, Inc. Method and apparatus for personalized physiologic parameters
US8594806B2 (en) 2010-04-30 2013-11-26 Cyberonics, Inc. Recharging and communication lead for an implantable device
WO2012013342A2 (en) * 2010-07-27 2012-02-02 Md Start Sa Stimulation system with synchronized wireless electrode devices
EP2635344B1 (en) * 2010-11-03 2015-07-08 The Cleveland Clinic Foundation Apparatus for energy efficient stimulation
CN106902457B (en) 2011-01-28 2022-10-21 斯蒂维科技公司 Neurostimulator system
US9220897B2 (en) 2011-04-04 2015-12-29 Micron Devices Llc Implantable lead
CN103492022A (en) 2011-04-04 2014-01-01 斯蒂维科技公司 Implantable lead
US9579510B2 (en) 2011-07-19 2017-02-28 Cochlear Limited Implantable remote control
US9841403B2 (en) 2011-07-21 2017-12-12 Mayo Foundation For Medical Education And Research Differentiating analytes detected using fast scan cyclic voltammetry
EP2736592B1 (en) 2011-07-29 2018-01-10 Micron Devices LLC Remote control of power or polarity selection for a neural stimulator
EP2741810B1 (en) 2011-08-12 2021-03-31 Stimwave Technologies Incorporated Microwave field stimulator
US9242103B2 (en) 2011-09-15 2016-01-26 Micron Devices Llc Relay module for implant
US8634912B2 (en) 2011-11-04 2014-01-21 Pacesetter, Inc. Dual-chamber leadless intra-cardiac medical device with intra-cardiac extension
US8781605B2 (en) 2011-10-31 2014-07-15 Pacesetter, Inc. Unitary dual-chamber leadless intra-cardiac medical device and method of implanting same
US9017341B2 (en) 2011-10-31 2015-04-28 Pacesetter, Inc. Multi-piece dual-chamber leadless intra-cardiac medical device and method of implanting same
US8700181B2 (en) 2011-11-03 2014-04-15 Pacesetter, Inc. Single-chamber leadless intra-cardiac medical device with dual-chamber functionality and shaped stabilization intra-cardiac extension
US9265436B2 (en) 2011-11-04 2016-02-23 Pacesetter, Inc. Leadless intra-cardiac medical device with built-in telemetry system
US8996109B2 (en) 2012-01-17 2015-03-31 Pacesetter, Inc. Leadless intra-cardiac medical device with dual chamber sensing through electrical and/or mechanical sensing
WO2013070794A2 (en) 2011-11-07 2013-05-16 Abbott Diabetes Care Inc. Analyte monitoring device and methods
US9572983B2 (en) 2012-03-26 2017-02-21 Setpoint Medical Corporation Devices and methods for modulation of bone erosion
WO2013177006A2 (en) 2012-05-21 2013-11-28 Stimwave Technologies, Incorporated Methods and devices for modulating excitable tissue of the exiting spinal nerves
WO2013192206A1 (en) * 2012-06-18 2013-12-27 The Cleveland Clinic Foundation Dynamic compliance voltage for energy efficient stimulation
US9343923B2 (en) 2012-08-23 2016-05-17 Cyberonics, Inc. Implantable medical device with backscatter signal based communication
WO2014036449A1 (en) 2012-08-31 2014-03-06 Alfred E. Mann Foundation For Scientific Research Feedback controlled coil driver for inductive power transfer
US9968306B2 (en) 2012-09-17 2018-05-15 Abbott Diabetes Care Inc. Methods and apparatuses for providing adverse condition notification with enhanced wireless communication range in analyte monitoring systems
US9935498B2 (en) 2012-09-25 2018-04-03 Cyberonics, Inc. Communication efficiency with an implantable medical device using a circulator and a backscatter signal
US20150247797A1 (en) 2012-09-25 2015-09-03 Alfred E. Mann Foundation For Scientific Research Microchannel plasmon resonance biosensor
AU2013337780B2 (en) * 2012-10-31 2018-04-05 The Board Of Trustees Of The Leland Stanford Junior University Wireless implantable sensing devices
US20140163641A1 (en) * 2012-12-06 2014-06-12 National University Of Singapore Muscle stimulation system
US8670842B1 (en) 2012-12-14 2014-03-11 Pacesetter, Inc. Intra-cardiac implantable medical device
US9254393B2 (en) 2012-12-26 2016-02-09 Micron Devices Llc Wearable antenna assembly
US10029101B2 (en) 2013-01-09 2018-07-24 Mayo Foundation For Medical Education And Research Systems for the detection and delivery of neurochemical and electrical signals for functional restoration
US11207522B2 (en) 2013-01-25 2021-12-28 Medtronic, Inc. Notification indicative of a change in efficacy of therapy
AU2014232252B2 (en) 2013-03-15 2018-01-18 Alfred E. Mann Foundation For Scientific Research Current sensing multiple output current stimulators with fast turn on time
US9044614B2 (en) 2013-03-15 2015-06-02 Alfred E. Mann Foundation For Scientific Research High voltage monitoring successive approximation analog to digital converter
CN104602760B (en) 2013-05-03 2017-11-07 艾尔弗雷德·E·曼科学研究基金会 High reliability wire for embedded type device is welded
WO2014179811A1 (en) 2013-05-03 2014-11-06 Alfred E. Mann Foundation For Scientific Research Multi-branch stimulation electrode for subcutaneous field stimulation
CN105658276B (en) 2013-05-03 2018-10-02 艾尔弗雷德·E·曼科学研究基金会 Implantation material recharger is shaken hands system and method
AU2014296320B2 (en) 2013-07-29 2018-07-26 Alfred E. Mann Foundation For Scientific Research Implant charging field control through radio link
JP6503351B2 (en) 2013-07-29 2019-04-17 アルフレッド イー. マン ファウンデーション フォー サイエンティフィック リサーチ High efficiency magnetic link for implantable devices
CA3075310C (en) 2013-07-29 2022-04-05 Alfred E. Mann Foundation For Scientific Research Microprocessor controlled class e driver
US9694192B2 (en) 2013-10-04 2017-07-04 Boston Scientific Neuromodulation Corporation Implantable medical device with a primary and rechargeable battery
US9592391B2 (en) 2014-01-10 2017-03-14 Cardiac Pacemakers, Inc. Systems and methods for detecting cardiac arrhythmias
EP3092038B1 (en) 2014-01-10 2017-12-27 Cardiac Pacemakers, Inc. Methods and systems for improved communication between medical devices
US9345883B2 (en) 2014-02-14 2016-05-24 Boston Scientific Neuromodulation Corporation Rechargeable-battery implantable medical device having a primary battery active during a rechargeable-battery undervoltage condition
US10004913B2 (en) 2014-03-03 2018-06-26 The Board Of Trustees Of The Leland Stanford Junior University Methods and apparatus for power conversion and data transmission in implantable sensors, stimulators, and actuators
US10434329B2 (en) 2014-05-09 2019-10-08 The Board Of Trustees Of The Leland Stanford Junior University Autofocus wireless power transfer to implantable devices in freely moving animals
WO2015175572A1 (en) 2014-05-12 2015-11-19 Micron Devices Llc Remote rf power system with low profile transmitting antenna
US10390720B2 (en) 2014-07-17 2019-08-27 Medtronic, Inc. Leadless pacing system including sensing extension
US9986349B2 (en) 2014-07-17 2018-05-29 Cochlear Limited Magnetic user interface controls
US9399140B2 (en) 2014-07-25 2016-07-26 Medtronic, Inc. Atrial contraction detection by a ventricular leadless pacing device for atrio-synchronous ventricular pacing
US9808631B2 (en) 2014-08-06 2017-11-07 Cardiac Pacemakers, Inc. Communication between a plurality of medical devices using time delays between communication pulses to distinguish between symbols
US9694189B2 (en) 2014-08-06 2017-07-04 Cardiac Pacemakers, Inc. Method and apparatus for communicating between medical devices
US9757570B2 (en) 2014-08-06 2017-09-12 Cardiac Pacemakers, Inc. Communications in a medical device system
WO2016033197A2 (en) 2014-08-28 2016-03-03 Cardiac Pacemakers, Inc. Medical device with triggered blanking period
US11311725B2 (en) 2014-10-24 2022-04-26 Setpoint Medical Corporation Systems and methods for stimulating and/or monitoring loci in the brain to treat inflammation and to enhance vagus nerve stimulation
US9492669B2 (en) 2014-11-11 2016-11-15 Medtronic, Inc. Mode switching by a ventricular leadless pacing device
US9492668B2 (en) 2014-11-11 2016-11-15 Medtronic, Inc. Mode switching by a ventricular leadless pacing device
US9623234B2 (en) 2014-11-11 2017-04-18 Medtronic, Inc. Leadless pacing device implantation
US9724519B2 (en) 2014-11-11 2017-08-08 Medtronic, Inc. Ventricular leadless pacing device mode switching
US9289612B1 (en) 2014-12-11 2016-03-22 Medtronic Inc. Coordination of ventricular pacing in a leadless pacing system
WO2016126807A1 (en) 2015-02-03 2016-08-11 Setpoint Medical Corporation Apparatus and method for reminding, prompting, or alerting a patient with an implanted stimulator
US10220213B2 (en) 2015-02-06 2019-03-05 Cardiac Pacemakers, Inc. Systems and methods for safe delivery of electrical stimulation therapy
WO2016126613A1 (en) 2015-02-06 2016-08-11 Cardiac Pacemakers, Inc. Systems and methods for treating cardiac arrhythmias
US10046167B2 (en) 2015-02-09 2018-08-14 Cardiac Pacemakers, Inc. Implantable medical device with radiopaque ID tag
US9901293B2 (en) * 2015-02-24 2018-02-27 Senseonics, Incorporated Analyte sensor
CN107530002B (en) 2015-03-04 2021-04-30 心脏起搏器股份公司 System and method for treating cardiac arrhythmias
US10213610B2 (en) 2015-03-18 2019-02-26 Cardiac Pacemakers, Inc. Communications in a medical device system with link quality assessment
US10050700B2 (en) 2015-03-18 2018-08-14 Cardiac Pacemakers, Inc. Communications in a medical device system with temporal optimization
EP3285694B1 (en) 2015-04-20 2021-03-10 Ossur Iceland EHF Electromyography with prosthetic or orthotic devices
JP6946261B2 (en) 2015-07-10 2021-10-06 アクソニクス インコーポレイテッド Implantable nerve stimulators and methods with internal electronics without ASICs
CN108136187B (en) 2015-08-20 2021-06-29 心脏起搏器股份公司 System and method for communication between medical devices
WO2017031221A1 (en) 2015-08-20 2017-02-23 Cardiac Pacemakers, Inc. Systems and methods for communication between medical devices
US9956414B2 (en) 2015-08-27 2018-05-01 Cardiac Pacemakers, Inc. Temporal configuration of a motion sensor in an implantable medical device
US9968787B2 (en) 2015-08-27 2018-05-15 Cardiac Pacemakers, Inc. Spatial configuration of a motion sensor in an implantable medical device
US10226631B2 (en) 2015-08-28 2019-03-12 Cardiac Pacemakers, Inc. Systems and methods for infarct detection
US10159842B2 (en) 2015-08-28 2018-12-25 Cardiac Pacemakers, Inc. System and method for detecting tamponade
US10137305B2 (en) 2015-08-28 2018-11-27 Cardiac Pacemakers, Inc. Systems and methods for behaviorally responsive signal detection and therapy delivery
US9956394B2 (en) 2015-09-10 2018-05-01 Boston Scientific Neuromodulation Corporation Connectors for electrical stimulation systems and methods of making and using
WO2017044389A1 (en) 2015-09-11 2017-03-16 Cardiac Pacemakers, Inc. Arrhythmia detection and confirmation
EP3359251B1 (en) 2015-10-08 2019-08-07 Cardiac Pacemakers, Inc. Adjusting pacing rates in an implantable medical device
WO2017106693A1 (en) 2015-12-17 2017-06-22 Cardiac Pacemakers, Inc. Conducted communication in a medical device system
US10905886B2 (en) 2015-12-28 2021-02-02 Cardiac Pacemakers, Inc. Implantable medical device for deployment across the atrioventricular septum
US10596367B2 (en) 2016-01-13 2020-03-24 Setpoint Medical Corporation Systems and methods for establishing a nerve block
US10342983B2 (en) 2016-01-14 2019-07-09 Boston Scientific Neuromodulation Corporation Systems and methods for making and using connector contact arrays for electrical stimulation systems
WO2017127548A1 (en) 2016-01-19 2017-07-27 Cardiac Pacemakers, Inc. Devices for wirelessly recharging a rechargeable battery of an implantable medical device
US11471681B2 (en) 2016-01-20 2022-10-18 Setpoint Medical Corporation Batteryless implantable microstimulators
US10314501B2 (en) 2016-01-20 2019-06-11 Setpoint Medical Corporation Implantable microstimulators and inductive charging systems
WO2017127756A1 (en) 2016-01-20 2017-07-27 Setpoint Medical Corporation Control of vagal stimulation
US10583304B2 (en) 2016-01-25 2020-03-10 Setpoint Medical Corporation Implantable neurostimulator having power control and thermal regulation and methods of use
CN108697886B (en) 2016-01-29 2022-11-08 艾克索尼克斯股份有限公司 Method and system for frequency adjustment to optimize charging of an implantable neurostimulator
CN109069840B (en) 2016-02-04 2022-03-15 心脏起搏器股份公司 Delivery system with force sensor for leadless cardiac devices
EP3436142A1 (en) 2016-03-31 2019-02-06 Cardiac Pacemakers, Inc. Implantable medical device with rechargeable battery
US10328272B2 (en) 2016-05-10 2019-06-25 Cardiac Pacemakers, Inc. Retrievability for implantable medical devices
US10668294B2 (en) 2016-05-10 2020-06-02 Cardiac Pacemakers, Inc. Leadless cardiac pacemaker configured for over the wire delivery
US10201713B2 (en) 2016-06-20 2019-02-12 Boston Scientific Neuromodulation Corporation Threaded connector assembly and methods of making and using the same
EP3474945B1 (en) 2016-06-27 2022-12-28 Cardiac Pacemakers, Inc. Cardiac therapy system using subcutaneously sensed p-waves for resynchronization pacing management
WO2018009569A1 (en) 2016-07-06 2018-01-11 Cardiac Pacemakers, Inc. Method and system for determining an atrial contraction timing fiducial in a leadless cardiac pacemaker system
WO2018009392A1 (en) 2016-07-07 2018-01-11 Cardiac Pacemakers, Inc. Leadless pacemaker using pressure measurements for pacing capture verification
US10307602B2 (en) 2016-07-08 2019-06-04 Boston Scientific Neuromodulation Corporation Threaded connector assembly and methods of making and using the same
WO2018017226A1 (en) 2016-07-20 2018-01-25 Cardiac Pacemakers, Inc. System for utilizing an atrial contraction timing fiducial in a leadless cardiac pacemaker system
EP3500342B1 (en) 2016-08-19 2020-05-13 Cardiac Pacemakers, Inc. Trans-septal implantable medical device
CN109640809B (en) 2016-08-24 2021-08-17 心脏起搏器股份公司 Integrated multi-device cardiac resynchronization therapy using P-wave to pacing timing
WO2018039322A1 (en) 2016-08-24 2018-03-01 Cardiac Pacemakers, Inc. Cardiac resynchronization using fusion promotion for timing management
US10758737B2 (en) 2016-09-21 2020-09-01 Cardiac Pacemakers, Inc. Using sensor data from an intracardially implanted medical device to influence operation of an extracardially implantable cardioverter
US10994145B2 (en) 2016-09-21 2021-05-04 Cardiac Pacemakers, Inc. Implantable cardiac monitor
WO2018057318A1 (en) 2016-09-21 2018-03-29 Cardiac Pacemakers, Inc. Leadless stimulation device with a housing that houses internal components of the leadless stimulation device and functions as the battery case and a terminal of an internal battery
US10543374B2 (en) 2016-09-30 2020-01-28 Boston Scientific Neuromodulation Corporation Connector assemblies with bending limiters for electrical stimulation systems and methods of making and using same
US10413733B2 (en) 2016-10-27 2019-09-17 Cardiac Pacemakers, Inc. Implantable medical device with gyroscope
WO2018081133A1 (en) 2016-10-27 2018-05-03 Cardiac Pacemakers, Inc. Implantable medical device having a sense channel with performance adjustment
EP3532160B1 (en) 2016-10-27 2023-01-25 Cardiac Pacemakers, Inc. Separate device in managing the pace pulse energy of a cardiac pacemaker
US10463305B2 (en) 2016-10-27 2019-11-05 Cardiac Pacemakers, Inc. Multi-device cardiac resynchronization therapy with timing enhancements
WO2018081017A1 (en) 2016-10-27 2018-05-03 Cardiac Pacemakers, Inc. Implantable medical device with pressure sensor
WO2018081225A1 (en) 2016-10-27 2018-05-03 Cardiac Pacemakers, Inc. Implantable medical device delivery system with integrated sensor
US10434317B2 (en) 2016-10-31 2019-10-08 Cardiac Pacemakers, Inc. Systems and methods for activity level pacing
WO2018081713A1 (en) 2016-10-31 2018-05-03 Cardiac Pacemakers, Inc Systems for activity level pacing
US10583301B2 (en) 2016-11-08 2020-03-10 Cardiac Pacemakers, Inc. Implantable medical device for atrial deployment
EP3538213B1 (en) 2016-11-09 2023-04-12 Cardiac Pacemakers, Inc. Systems and devices for setting cardiac pacing pulse parameters for a cardiac pacing device
US10894163B2 (en) 2016-11-21 2021-01-19 Cardiac Pacemakers, Inc. LCP based predictive timing for cardiac resynchronization
US10639486B2 (en) 2016-11-21 2020-05-05 Cardiac Pacemakers, Inc. Implantable medical device with recharge coil
WO2018094342A1 (en) 2016-11-21 2018-05-24 Cardiac Pacemakers, Inc Implantable medical device with a magnetically permeable housing and an inductive coil disposed about the housing
US10881869B2 (en) 2016-11-21 2021-01-05 Cardiac Pacemakers, Inc. Wireless re-charge of an implantable medical device
WO2018094344A2 (en) 2016-11-21 2018-05-24 Cardiac Pacemakers, Inc Leadless cardiac pacemaker with multimode communication
US11207532B2 (en) 2017-01-04 2021-12-28 Cardiac Pacemakers, Inc. Dynamic sensing updates using postural input in a multiple device cardiac rhythm management system
EP3573706A1 (en) 2017-01-26 2019-12-04 Cardiac Pacemakers, Inc. Intra-body device communication with redundant message transmission
US10737102B2 (en) 2017-01-26 2020-08-11 Cardiac Pacemakers, Inc. Leadless implantable device with detachable fixation
EP3573709A1 (en) 2017-01-26 2019-12-04 Cardiac Pacemakers, Inc. Leadless device with overmolded components
US10905871B2 (en) 2017-01-27 2021-02-02 Boston Scientific Neuromodulation Corporation Lead assemblies with arrangements to confirm alignment between terminals and contacts
WO2018160495A1 (en) 2017-02-28 2018-09-07 Boston Scientific Neuromodulation Corporation Toolless connector for latching stimulation leads and methods of making and using
US10905872B2 (en) 2017-04-03 2021-02-02 Cardiac Pacemakers, Inc. Implantable medical device with a movable electrode biased toward an extended position
AU2018248361B2 (en) 2017-04-03 2020-08-27 Cardiac Pacemakers, Inc. Cardiac pacemaker with pacing pulse energy adjustment based on sensed heart rate
US10603499B2 (en) 2017-04-07 2020-03-31 Boston Scientific Neuromodulation Corporation Tapered implantable lead and connector interface and methods of making and using
US11040197B2 (en) 2017-06-22 2021-06-22 Mayo Foundation For Medical Education And Research Voltammetric neurochemical detection in whole blood
US10918873B2 (en) 2017-07-25 2021-02-16 Boston Scientific Neuromodulation Corporation Systems and methods for making and using an enhanced connector of an electrical stimulation system
US11173307B2 (en) 2017-08-14 2021-11-16 Setpoint Medical Corporation Vagus nerve stimulation pre-screening test
US10918875B2 (en) 2017-08-18 2021-02-16 Cardiac Pacemakers, Inc. Implantable medical device with a flux concentrator and a receiving coil disposed about the flux concentrator
US11065459B2 (en) 2017-08-18 2021-07-20 Cardiac Pacemakers, Inc. Implantable medical device with pressure sensor
EP3681587B1 (en) 2017-09-15 2023-08-23 Boston Scientific Neuromodulation Corporation Actuatable lead connector for an operating room cable assembly
EP3681588B1 (en) 2017-09-15 2023-05-10 Boston Scientific Neuromodulation Corporation Biased lead connector for operating room cable assembly
EP3684465B1 (en) 2017-09-20 2021-07-14 Cardiac Pacemakers, Inc. Implantable medical device with multiple modes of operation
US11139603B2 (en) 2017-10-03 2021-10-05 Boston Scientific Neuromodulation Corporation Connectors with spring contacts for electrical stimulation systems and methods of making and using same
US11185703B2 (en) 2017-11-07 2021-11-30 Cardiac Pacemakers, Inc. Leadless cardiac pacemaker for bundle of his pacing
EP3717059A1 (en) 2017-12-01 2020-10-07 Cardiac Pacemakers, Inc. Methods and systems for detecting atrial contraction timing fiducials within a search window from a ventricularly implanted leadless cardiac pacemaker
EP3717064B1 (en) 2017-12-01 2023-06-07 Cardiac Pacemakers, Inc. Methods and systems for detecting atrial contraction timing fiducials during ventricular filling from a ventricularly implanted leadless cardiac pacemaker
CN111432875A (en) 2017-12-01 2020-07-17 心脏起搏器股份公司 Method and system for detecting atrial contraction timing references and determining cardiac intervals from a ventricular-implantable leadless cardiac pacemaker
WO2019108830A1 (en) 2017-12-01 2019-06-06 Cardiac Pacemakers, Inc. Leadless cardiac pacemaker with reversionary behavior
US11529523B2 (en) 2018-01-04 2022-12-20 Cardiac Pacemakers, Inc. Handheld bridge device for providing a communication bridge between an implanted medical device and a smartphone
WO2019136148A1 (en) 2018-01-04 2019-07-11 Cardiac Pacemakers, Inc. Dual chamber pacing without beat-to-beat communication
US11103712B2 (en) 2018-01-16 2021-08-31 Boston Scientific Neuromodulation Corporation Connector assemblies with novel spacers for electrical stimulation systems and methods of making and using same
JP2021518249A (en) 2018-03-20 2021-08-02 セカンド・ハート・アシスト・インコーポレイテッド Circulation auxiliary pump
EP3768160B1 (en) 2018-03-23 2023-06-07 Medtronic, Inc. Vfa cardiac therapy for tachycardia
JP2021518192A (en) 2018-03-23 2021-08-02 メドトロニック,インコーポレイテッド VfA cardiac resynchronization therapy
US11400296B2 (en) 2018-03-23 2022-08-02 Medtronic, Inc. AV synchronous VfA cardiac therapy
US11052259B2 (en) 2018-05-11 2021-07-06 Boston Scientific Neuromodulation Corporation Connector assembly for an electrical stimulation system and methods of making and using
US10736509B2 (en) 2018-07-30 2020-08-11 Biosense Webster (Israel) Ltd. Dual frequency control for a physiologic monitor
US11260229B2 (en) 2018-09-25 2022-03-01 The Feinstein Institutes For Medical Research Methods and apparatuses for reducing bleeding via coordinated trigeminal and vagal nerve stimulation
WO2020065582A1 (en) 2018-09-26 2020-04-02 Medtronic, Inc. Capture in ventricle-from-atrium cardiac therapy
US11679265B2 (en) 2019-02-14 2023-06-20 Medtronic, Inc. Lead-in-lead systems and methods for cardiac therapy
WO2020185902A1 (en) 2019-03-11 2020-09-17 Axonics Modulation Technologies, Inc. Charging device with off-center coil
US11833349B2 (en) 2019-03-29 2023-12-05 Cardiac Pacemakers, Inc. Systems and methods for treating cardiac arrhythmias
US11446510B2 (en) 2019-03-29 2022-09-20 Cardiac Pacemakers, Inc. Systems and methods for treating cardiac arrhythmias
US11697025B2 (en) 2019-03-29 2023-07-11 Medtronic, Inc. Cardiac conduction system capture
US11213676B2 (en) 2019-04-01 2022-01-04 Medtronic, Inc. Delivery systems for VfA cardiac therapy
US11357992B2 (en) 2019-05-03 2022-06-14 Boston Scientific Neuromodulation Corporation Connector assembly for an electrical stimulation system and methods of making and using
US11712188B2 (en) 2019-05-07 2023-08-01 Medtronic, Inc. Posterior left bundle branch engagement
WO2020242900A1 (en) 2019-05-24 2020-12-03 Axonics Modulation Technologies, Inc. Trainer device for a neurostimulator programmer and associated methods of use with a neurostimulation system
US11305127B2 (en) 2019-08-26 2022-04-19 Medtronic Inc. VfA delivery and implant region detection
US11571582B2 (en) 2019-09-11 2023-02-07 Cardiac Pacemakers, Inc. Tools and systems for implanting and/or retrieving a leadless cardiac pacing device with helix fixation
CN114364431A (en) 2019-09-11 2022-04-15 心脏起搏器股份公司 Tool and system for implanting and/or retrieving a leadless cardiac pacing device having a helical fixation member
US11813466B2 (en) 2020-01-27 2023-11-14 Medtronic, Inc. Atrioventricular nodal stimulation
US11911168B2 (en) 2020-04-03 2024-02-27 Medtronic, Inc. Cardiac conduction system therapy benefit determination
US11813464B2 (en) 2020-07-31 2023-11-14 Medtronic, Inc. Cardiac conduction system evaluation

Citations (53)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US558640A (en) * 1896-04-21 Animal-clipping machine
US4041954A (en) * 1974-05-07 1977-08-16 Kabushiki Kaisha Daini Seikosha System for detecting information in an artificial cardiac pacemaker
US4146029A (en) * 1974-04-23 1979-03-27 Ellinwood Jr Everett H Self-powered implanted programmable medication system and method
US4360019A (en) * 1979-02-28 1982-11-23 Andros Incorporated Implantable infusion device
US4414979A (en) * 1981-02-23 1983-11-15 Telectronics Pty. Ltd. Monitorable bone growth stimulator
US4543955A (en) * 1983-08-01 1985-10-01 Cordis Corporation System for controlling body implantable action device
US4612934A (en) * 1981-06-30 1986-09-23 Borkan William N Non-invasive multiprogrammable tissue stimulator
US4619653A (en) * 1979-04-27 1986-10-28 The Johns Hopkins University Apparatus for detecting at least one predetermined condition and providing an informational signal in response thereto in a medication infusion system
US4714462A (en) * 1986-02-03 1987-12-22 Intermedics Infusaid, Inc. Positive pressure programmable infusion pump
US4886064A (en) * 1987-11-25 1989-12-12 Siemens Aktiengesellschaft Body activity controlled heart pacer
US4925443A (en) * 1987-02-27 1990-05-15 Heilman Marlin S Biocompatible ventricular assist and arrhythmia control device
US5113859A (en) * 1988-09-19 1992-05-19 Medtronic, Inc. Acoustic body bus medical device communication system
US5167625A (en) * 1990-10-09 1992-12-01 Sarcos Group Multiple vesicle implantable drug delivery system
US5170801A (en) * 1990-10-02 1992-12-15 Glaxo Inc. Medical capsule device actuated by radio-frequency (rf) signal
US5193540A (en) * 1991-12-18 1993-03-16 Alfred E. Mann Foundation For Scientific Research Structure and method of manufacture of an implantable microstimulator
US5279607A (en) * 1991-05-30 1994-01-18 The State University Of New York Telemetry capsule and process
US5312446A (en) * 1992-08-26 1994-05-17 Medtronic, Inc. Compressed storage of data in cardiac pacemakers
US5312439A (en) * 1991-12-12 1994-05-17 Loeb Gerald E Implantable device having an electrolytic storage electrode
US5314457A (en) * 1993-04-08 1994-05-24 Jeutter Dean C Regenerative electrical
US5314453A (en) * 1991-12-06 1994-05-24 Spinal Cord Society Position sensitive power transfer antenna
US5318593A (en) * 1978-07-20 1994-06-07 Medtronic, Inc. Multi-mode adaptable implantable pacemaker
US5324316A (en) * 1991-12-18 1994-06-28 Alfred E. Mann Foundation For Scientific Research Implantable microstimulator
US5358514A (en) * 1991-12-18 1994-10-25 Alfred E. Mann Foundation For Scientific Research Implantable microdevice with self-attaching electrodes
US5397350A (en) * 1993-05-03 1995-03-14 Chow; Alan Y. Independent photoelectric artificial retina device and method of using same
US5411537A (en) * 1993-10-29 1995-05-02 Intermedics, Inc. Rechargeable biomedical battery powered devices with recharging and control system therefor
US5411535A (en) * 1992-03-03 1995-05-02 Terumo Kabushiki Kaisha Cardiac pacemaker using wireless transmission
US5443486A (en) * 1994-09-26 1995-08-22 Medtronic, Inc. Method and apparatus to limit control of parameters of electrical tissue stimulators
US5481262A (en) * 1990-08-03 1996-01-02 Bio Medic Data Systems, Inc. System monitoring programmable implanatable transponder
US5507737A (en) * 1993-04-22 1996-04-16 Siemens Elema Ab Apparatus for determining the volume of a bellows reservoir for medication in an implantable infusion system
US5544651A (en) * 1992-09-08 1996-08-13 Wilk; Peter J. Medical system and associated method for automatic treatment
US5562713A (en) * 1995-01-18 1996-10-08 Pacesetter, Inc. Bidirectional telemetry apparatus and method for implantable device
US5571148A (en) * 1994-08-10 1996-11-05 Loeb; Gerald E. Implantable multichannel stimulator
US5591217A (en) * 1995-01-04 1997-01-07 Plexus, Inc. Implantable stimulator with replenishable, high value capacitive power source and method therefor
US5626630A (en) * 1994-10-13 1997-05-06 Ael Industries, Inc. Medical telemetry system using an implanted passive transponder
US5694952A (en) * 1994-12-15 1997-12-09 Pacesetter Ab Magnetic field detector
US5725559A (en) * 1996-05-16 1998-03-10 Intermedics Inc. Programmably upgradable implantable medical device
US5728154A (en) * 1996-02-29 1998-03-17 Minnesota Mining And Manfacturing Company Communication method for implantable medical device
US5733313A (en) * 1996-08-01 1998-03-31 Exonix Corporation RF coupled, implantable medical device with rechargeable back-up power source
US5749909A (en) * 1996-11-07 1998-05-12 Sulzer Intermedics Inc. Transcutaneous energy coupling using piezoelectric device
US5759199A (en) * 1995-08-02 1998-06-02 Pacesetter, Inc. System and method for ambulatory monitoring and programming of an implantable medical device
US5766231A (en) * 1992-02-20 1998-06-16 Neomedics, Inc. Implantable growth tissue stimulator and method of operation
US5782799A (en) * 1997-02-07 1998-07-21 Sarcos, Inc. Method for automatic dosing of drugs
US5810735A (en) * 1995-02-27 1998-09-22 Medtronic, Inc. External patient reference sensors
US5814089A (en) * 1996-12-18 1998-09-29 Medtronic, Inc. Leadless multisite implantable stimulus and diagnostic system
US6051017A (en) * 1996-02-20 2000-04-18 Advanced Bionics Corporation Implantable microstimulator and systems employing the same
US6061596A (en) * 1995-11-24 2000-05-09 Advanced Bionics Corporation Method for conditioning pelvic musculature using an implanted microstimulator
US6122284A (en) * 1997-07-07 2000-09-19 Telcom Semiconductor, Inc. Multidrop analog signal bus
US6185452B1 (en) * 1997-02-26 2001-02-06 Joseph H. Schulman Battery-powered patient implantable device
US6208894B1 (en) * 1997-02-26 2001-03-27 Alfred E. Mann Foundation For Scientific Research And Advanced Bionics System of implantable devices for monitoring and/or affecting body parameters
US6564807B1 (en) * 1997-02-26 2003-05-20 Alfred E. Mann Foundation For Scientific Research System of implantable devices for monitoring and/or affecting body parameters
US20040059392A1 (en) * 2002-06-28 2004-03-25 Jordi Parramon Microstimulator having self-contained power source
US6733485B1 (en) * 2001-05-25 2004-05-11 Advanced Bionics Corporation Microstimulator-based electrochemotherapy methods and systems
US7114502B2 (en) * 1997-02-26 2006-10-03 Alfred E. Mann Foundation For Scientific Research Battery-powered patient implantable device

Family Cites Families (13)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4006748A (en) * 1976-01-29 1977-02-08 Pacestter Systems, Inc. Implantable unipolar pacemaker with improved outer electrode plate
US4142533A (en) * 1976-10-28 1979-03-06 Research Corporation Monitoring system for cardiac pacers
US4281664A (en) * 1979-05-14 1981-08-04 Medtronic, Inc. Implantable telemetry transmission system for analog and digital data
US4741341A (en) * 1986-03-12 1988-05-03 Siemens-Pacesetter, Inc. Protection circuit and method for implanted ECG telemetry circuits
US4888064A (en) * 1986-09-15 1989-12-19 General Electric Company Method of forming strong fatigue crack resistant nickel base superalloy and product formed
DE3932405A1 (en) 1989-09-28 1991-04-11 Bodenseewerk Geraetetech Control system for neuro-protheses - has inertial sensors coupled to regulating loop for improved control
US5113869A (en) 1990-08-21 1992-05-19 Telectronics Pacing Systems, Inc. Implantable ambulatory electrocardiogram monitor
US5222494A (en) * 1991-07-31 1993-06-29 Cyberonics, Inc. Implantable tissue stimulator output stabilization system
EP0561068B1 (en) 1992-02-20 1999-03-03 Neomedics, Inc. Implantable bone growth stimulator
US5814077A (en) * 1992-11-13 1998-09-29 Pacesetter, Inc. Pacemaker and method of operating same that provides functional atrial cardiac pacing with ventricular support
EP0672427A1 (en) 1994-03-17 1995-09-20 Siemens-Elema AB System for infusion of medicine into the body of a patient
US5476487A (en) * 1994-12-28 1995-12-19 Pacesetter, Inc. Autothreshold assessment in an implantable pacemaker
CA2297022A1 (en) * 1997-08-01 1999-02-11 Alfred E. Mann Foundation For Scientific Research Implantable device with improved battery recharging and powering configuration

Patent Citations (56)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US558640A (en) * 1896-04-21 Animal-clipping machine
US4146029A (en) * 1974-04-23 1979-03-27 Ellinwood Jr Everett H Self-powered implanted programmable medication system and method
US4041954A (en) * 1974-05-07 1977-08-16 Kabushiki Kaisha Daini Seikosha System for detecting information in an artificial cardiac pacemaker
US5318593A (en) * 1978-07-20 1994-06-07 Medtronic, Inc. Multi-mode adaptable implantable pacemaker
US4360019A (en) * 1979-02-28 1982-11-23 Andros Incorporated Implantable infusion device
US4619653A (en) * 1979-04-27 1986-10-28 The Johns Hopkins University Apparatus for detecting at least one predetermined condition and providing an informational signal in response thereto in a medication infusion system
US4414979A (en) * 1981-02-23 1983-11-15 Telectronics Pty. Ltd. Monitorable bone growth stimulator
US4612934A (en) * 1981-06-30 1986-09-23 Borkan William N Non-invasive multiprogrammable tissue stimulator
US4543955A (en) * 1983-08-01 1985-10-01 Cordis Corporation System for controlling body implantable action device
US4714462A (en) * 1986-02-03 1987-12-22 Intermedics Infusaid, Inc. Positive pressure programmable infusion pump
US4925443A (en) * 1987-02-27 1990-05-15 Heilman Marlin S Biocompatible ventricular assist and arrhythmia control device
US4886064A (en) * 1987-11-25 1989-12-12 Siemens Aktiengesellschaft Body activity controlled heart pacer
US5113859A (en) * 1988-09-19 1992-05-19 Medtronic, Inc. Acoustic body bus medical device communication system
US5481262A (en) * 1990-08-03 1996-01-02 Bio Medic Data Systems, Inc. System monitoring programmable implanatable transponder
US5170801A (en) * 1990-10-02 1992-12-15 Glaxo Inc. Medical capsule device actuated by radio-frequency (rf) signal
US5167625A (en) * 1990-10-09 1992-12-01 Sarcos Group Multiple vesicle implantable drug delivery system
US5279607A (en) * 1991-05-30 1994-01-18 The State University Of New York Telemetry capsule and process
US5314453A (en) * 1991-12-06 1994-05-24 Spinal Cord Society Position sensitive power transfer antenna
US5312439A (en) * 1991-12-12 1994-05-17 Loeb Gerald E Implantable device having an electrolytic storage electrode
US5193540A (en) * 1991-12-18 1993-03-16 Alfred E. Mann Foundation For Scientific Research Structure and method of manufacture of an implantable microstimulator
US5324316A (en) * 1991-12-18 1994-06-28 Alfred E. Mann Foundation For Scientific Research Implantable microstimulator
US5358514A (en) * 1991-12-18 1994-10-25 Alfred E. Mann Foundation For Scientific Research Implantable microdevice with self-attaching electrodes
US5405367A (en) * 1991-12-18 1995-04-11 Alfred E. Mann Foundation For Scientific Research Structure and method of manufacture of an implantable microstimulator
US5766231A (en) * 1992-02-20 1998-06-16 Neomedics, Inc. Implantable growth tissue stimulator and method of operation
US5411535A (en) * 1992-03-03 1995-05-02 Terumo Kabushiki Kaisha Cardiac pacemaker using wireless transmission
US5312446A (en) * 1992-08-26 1994-05-17 Medtronic, Inc. Compressed storage of data in cardiac pacemakers
US5544651A (en) * 1992-09-08 1996-08-13 Wilk; Peter J. Medical system and associated method for automatic treatment
US5314457A (en) * 1993-04-08 1994-05-24 Jeutter Dean C Regenerative electrical
US5507737A (en) * 1993-04-22 1996-04-16 Siemens Elema Ab Apparatus for determining the volume of a bellows reservoir for medication in an implantable infusion system
US5397350A (en) * 1993-05-03 1995-03-14 Chow; Alan Y. Independent photoelectric artificial retina device and method of using same
US5411537A (en) * 1993-10-29 1995-05-02 Intermedics, Inc. Rechargeable biomedical battery powered devices with recharging and control system therefor
US5571148A (en) * 1994-08-10 1996-11-05 Loeb; Gerald E. Implantable multichannel stimulator
US5443486A (en) * 1994-09-26 1995-08-22 Medtronic, Inc. Method and apparatus to limit control of parameters of electrical tissue stimulators
US5626630A (en) * 1994-10-13 1997-05-06 Ael Industries, Inc. Medical telemetry system using an implanted passive transponder
US5694952A (en) * 1994-12-15 1997-12-09 Pacesetter Ab Magnetic field detector
US5807397A (en) * 1995-01-04 1998-09-15 Plexus, Inc. Implantable stimulator with replenishable, high value capacitive power source and method therefor
US5591217A (en) * 1995-01-04 1997-01-07 Plexus, Inc. Implantable stimulator with replenishable, high value capacitive power source and method therefor
US5562713A (en) * 1995-01-18 1996-10-08 Pacesetter, Inc. Bidirectional telemetry apparatus and method for implantable device
US5810735A (en) * 1995-02-27 1998-09-22 Medtronic, Inc. External patient reference sensors
US5759199A (en) * 1995-08-02 1998-06-02 Pacesetter, Inc. System and method for ambulatory monitoring and programming of an implantable medical device
US6061596A (en) * 1995-11-24 2000-05-09 Advanced Bionics Corporation Method for conditioning pelvic musculature using an implanted microstimulator
US6051017A (en) * 1996-02-20 2000-04-18 Advanced Bionics Corporation Implantable microstimulator and systems employing the same
US5728154A (en) * 1996-02-29 1998-03-17 Minnesota Mining And Manfacturing Company Communication method for implantable medical device
US5725559A (en) * 1996-05-16 1998-03-10 Intermedics Inc. Programmably upgradable implantable medical device
US5733313A (en) * 1996-08-01 1998-03-31 Exonix Corporation RF coupled, implantable medical device with rechargeable back-up power source
US5749909A (en) * 1996-11-07 1998-05-12 Sulzer Intermedics Inc. Transcutaneous energy coupling using piezoelectric device
US5814089A (en) * 1996-12-18 1998-09-29 Medtronic, Inc. Leadless multisite implantable stimulus and diagnostic system
US5782799A (en) * 1997-02-07 1998-07-21 Sarcos, Inc. Method for automatic dosing of drugs
US6185452B1 (en) * 1997-02-26 2001-02-06 Joseph H. Schulman Battery-powered patient implantable device
US6208894B1 (en) * 1997-02-26 2001-03-27 Alfred E. Mann Foundation For Scientific Research And Advanced Bionics System of implantable devices for monitoring and/or affecting body parameters
US6315721B2 (en) * 1997-02-26 2001-11-13 Alfred E. Mann Foundation For Scientific Research System of implantable devices for monitoring and/or affecting body parameters
US6564807B1 (en) * 1997-02-26 2003-05-20 Alfred E. Mann Foundation For Scientific Research System of implantable devices for monitoring and/or affecting body parameters
US7114502B2 (en) * 1997-02-26 2006-10-03 Alfred E. Mann Foundation For Scientific Research Battery-powered patient implantable device
US6122284A (en) * 1997-07-07 2000-09-19 Telcom Semiconductor, Inc. Multidrop analog signal bus
US6733485B1 (en) * 2001-05-25 2004-05-11 Advanced Bionics Corporation Microstimulator-based electrochemotherapy methods and systems
US20040059392A1 (en) * 2002-06-28 2004-03-25 Jordi Parramon Microstimulator having self-contained power source

Cited By (102)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20050075682A1 (en) * 1997-02-26 2005-04-07 Schulman Joseph H. Neural device for sensing temperature
US20050137648A1 (en) * 1997-02-26 2005-06-23 Gregoire Cosendai System and method suitable for treatment of a patient with a neurological deficit by sequentially stimulating neural pathways using a system of discrete implantable medical devices
US7460911B2 (en) * 1997-02-26 2008-12-02 Alfred E. Mann Foundation For Scientific Research System and method suitable for treatment of a patient with a neurological deficit by sequentially stimulating neural pathways using a system of discrete implantable medical devices
US20050032511A1 (en) * 2003-08-07 2005-02-10 Cardiac Pacemakers, Inc. Wireless firmware download to an external device
US8489196B2 (en) 2003-10-03 2013-07-16 Medtronic, Inc. System, apparatus and method for interacting with a targeted tissue of a patient
US20070106175A1 (en) * 2004-03-25 2007-05-10 Akio Uchiyama In-vivo information acquisition apparatus and in-vivo information acquisition apparatus system
US8343069B2 (en) * 2004-03-25 2013-01-01 Olympus Corporation In-vivo information acquisition apparatus and in-vivo information acquisition apparatus system
US8195276B2 (en) 2004-03-25 2012-06-05 Olympus Corporation In-vivo information acquisition apparatus and in-vivo information acquisition apparatus system
US20090124872A1 (en) * 2004-03-25 2009-05-14 Olympus Corporation In-vivo information acquisition apparatus and in-vivo information acquisition apparatus system
EP1839562A1 (en) * 2004-03-25 2007-10-03 Olympus Corporation In-vivo information acquisition apparatus and in-vivo information acquisition apparatus system
US8176922B2 (en) 2004-06-29 2012-05-15 Depuy Products, Inc. System and method for bidirectional communication with an implantable medical device using an implant component as an antenna
US20060009856A1 (en) * 2004-06-29 2006-01-12 Sherman Jason T System and method for bidirectional communication with an implantable medical device using an implant component as an antenna
US10575140B2 (en) 2004-12-29 2020-02-25 DePuy Synthes Products, Inc. Medical device communications network
US8001975B2 (en) 2004-12-29 2011-08-23 Depuy Products, Inc. Medical device communications network
US20060140139A1 (en) * 2004-12-29 2006-06-29 Disilvestro Mark R Medical device communications network
US20110136521A1 (en) * 2004-12-29 2011-06-09 Depuy Products, Inc. Medical Device Communications Network
US9860717B2 (en) 2004-12-29 2018-01-02 DePuy Synthes Products, Inc. Medical device communications network
US9560969B2 (en) 2004-12-29 2017-02-07 DePuy Synthes Products, Inc. Medical device communications network
EP1676525A1 (en) * 2004-12-29 2006-07-05 DePuy Products, Inc. Medical device communications network
WO2006113654A1 (en) * 2005-04-18 2006-10-26 Bioness Development, Llc System and related method for determining a measurement between locations on a body
US20080319349A1 (en) * 2005-04-18 2008-12-25 Yitzhak Zilberman System and Related Method For Determining a Measurement Between Locations on a Body
US9358400B2 (en) 2005-10-14 2016-06-07 Pacesetter, Inc. Leadless cardiac pacemaker
US10238883B2 (en) 2005-10-14 2019-03-26 Pacesetter Inc. Leadless cardiac pacemaker system for usage in combination with an implantable cardioverter-defibrillator
US20110071586A1 (en) * 2005-10-14 2011-03-24 Nanostim, Inc. Leadless Cardiac Pacemaker Triggered by Conductive Communication
US9687666B2 (en) 2005-10-14 2017-06-27 Pacesetter, Inc. Leadless cardiac pacemaker system for usage in combination with an implantable cardioverter-defibrillator
US7937148B2 (en) 2005-10-14 2011-05-03 Nanostim, Inc. Rate responsive leadless cardiac pacemaker
US7945333B2 (en) 2005-10-14 2011-05-17 Nanostim, Inc. Programmer for biostimulator system
US9872999B2 (en) 2005-10-14 2018-01-23 Pacesetter, Inc. Leadless cardiac pacemaker system for usage in combination with an implantable cardioverter-defibrillator
US9227077B2 (en) 2005-10-14 2016-01-05 Pacesetter, Inc. Leadless cardiac pacemaker triggered by conductive communication
WO2007047681A3 (en) * 2005-10-14 2008-09-25 Nanostim Inc Leadless cardiac pacemaker and system
US20110208260A1 (en) * 2005-10-14 2011-08-25 Nanostim, Inc. Rate Responsive Leadless Cardiac Pacemaker
US8010209B2 (en) 2005-10-14 2011-08-30 Nanostim, Inc. Delivery system for implantable biostimulator
US20110218587A1 (en) * 2005-10-14 2011-09-08 Nanostim, Inc. Programmer for Biostimulator System
US9216298B2 (en) 2005-10-14 2015-12-22 Pacesetter, Inc. Leadless cardiac pacemaker system with conductive communication
US9409033B2 (en) 2005-10-14 2016-08-09 Pacesetter, Inc. Leadless cardiac pacemaker system for usage in combination with an implantable cardioverter-defibrillator
WO2007047681A2 (en) * 2005-10-14 2007-04-26 Nanostim, Inc. Leadless cardiac pacemaker and system
US9192774B2 (en) 2005-10-14 2015-11-24 Pacesetter, Inc. Cardiac pacemaker system for usage in combination with an implantable cardioverter-defibrillator
US9168383B2 (en) 2005-10-14 2015-10-27 Pacesetter, Inc. Leadless cardiac pacemaker with conducted communication
US8295939B2 (en) 2005-10-14 2012-10-23 Nanostim, Inc. Programmer for biostimulator system
US20070088394A1 (en) * 2005-10-14 2007-04-19 Jacobson Peter M Leadless cardiac pacemaker system for usage in combination with an implantable cardioverter-defibrillator
US8352025B2 (en) 2005-10-14 2013-01-08 Nanostim, Inc. Leadless cardiac pacemaker triggered by conductive communication
US9072913B2 (en) 2005-10-14 2015-07-07 Pacesetter, Inc. Rate responsive leadless cardiac pacemaker
US8457742B2 (en) 2005-10-14 2013-06-04 Nanostim, Inc. Leadless cardiac pacemaker system for usage in combination with an implantable cardioverter-defibrillator
US20070088398A1 (en) * 2005-10-14 2007-04-19 Jacobson Peter M Leadless cardiac pacemaker triggered by conductive communication
US8855789B2 (en) 2005-10-14 2014-10-07 Pacesetter, Inc. Implantable biostimulator delivery system
US8798745B2 (en) 2005-10-14 2014-08-05 Pacesetter, Inc. Leadless cardiac pacemaker system for usage in combination with an implantable cardioverter-defibrillator
US8788035B2 (en) 2005-10-14 2014-07-22 Pacesetter, Inc. Leadless cardiac pacemaker triggered by conductive communication
US8788053B2 (en) 2005-10-14 2014-07-22 Pacesetter, Inc. Programmer for biostimulator system
US8712522B1 (en) * 2005-10-18 2014-04-29 Cvrx, Inc. System for setting programmable parameters for an implantable hypertension treatment device
US8977359B2 (en) 2005-10-18 2015-03-10 Cvrx, Inc. System for setting programmable parameters for an implantable hypertension treatment device
US8209036B2 (en) 2005-11-16 2012-06-26 Bioness Neuromodulation Ltd. Orthosis for a gait modulation system
US10080885B2 (en) 2005-11-16 2018-09-25 Bioness Neuromodulation Ltd. Orthosis for a gait modulation system
US8209022B2 (en) 2005-11-16 2012-06-26 Bioness Neuromodulation Ltd. Gait modulation system and method
US20110152968A1 (en) * 2005-11-16 2011-06-23 Bioness Neuromodulation Ltd. Orthosis for a gait modulation system
US8694110B2 (en) 2005-11-16 2014-04-08 Bioness Neuromodulation Ltd. Orthosis for gait modulation
US8972017B2 (en) 2005-11-16 2015-03-03 Bioness Neuromodulation Ltd. Gait modulation system and method
US20100168622A1 (en) * 2005-11-16 2010-07-01 Amit Dar Sensor device for gait enhancement
US10076656B2 (en) 2005-11-16 2018-09-18 Bioness Neuromodulation Ltd. Gait modulation system and method
US11058867B2 (en) 2005-11-16 2021-07-13 Bioness Neuromodulation Ltd. Orthosis for a gait modulation system
US8382688B2 (en) 2005-11-16 2013-02-26 Bioness Neuromodulation Ltd. Sensor device for gait enhancement
US9415205B2 (en) 2006-05-01 2016-08-16 Bioness Neuromodulation Ltd. Functional electrical stimulation systems
US8788049B2 (en) 2006-05-01 2014-07-22 Bioness Neuromodulation Ltd. Functional electrical stimulation systems
US11247048B2 (en) 2006-05-01 2022-02-15 Bioness Neuromodulation Ltd. Functional electrical stimulation systems
US10016598B2 (en) 2006-05-01 2018-07-10 Bioness Neuromodulation Ltd. Functional electrical stimulation systems
US20090069865A1 (en) * 2006-05-01 2009-03-12 Eyal Lasko Functional electrical stimulation systems
US10543365B2 (en) 2006-05-01 2020-01-28 Bioness Neuromodulation Ltd. Functional electrical stimulation systems
US20080132882A1 (en) * 2006-11-30 2008-06-05 Howmedica Osteonics Corp. Orthopedic instruments with RFID
US20080211302A1 (en) * 2007-02-09 2008-09-04 Takashi Hirota Assist device
US8585775B2 (en) 2007-02-09 2013-11-19 Semiconductor Energy Laboratory Co., Ltd. Assist device
US8080064B2 (en) 2007-06-29 2011-12-20 Depuy Products, Inc. Tibial tray assembly having a wireless communication device
US20110017610A1 (en) * 2007-09-03 2011-01-27 Alexander Hahn Device and process for breaking down pollutants in a liquid and also use of such a device
US20090082828A1 (en) * 2007-09-20 2009-03-26 Alan Ostroff Leadless Cardiac Pacemaker with Secondary Fixation Capability
US9272155B2 (en) 2009-02-02 2016-03-01 Pacesetter, Inc. Leadless cardiac pacemaker with secondary fixation capability
US20100198288A1 (en) * 2009-02-02 2010-08-05 Alan Ostroff Leadless Cardiac Pacemaker with Secondary Fixation Capability
US8527068B2 (en) 2009-02-02 2013-09-03 Nanostim, Inc. Leadless cardiac pacemaker with secondary fixation capability
US20110077708A1 (en) * 2009-09-28 2011-03-31 Alan Ostroff MRI Compatible Leadless Cardiac Pacemaker
US9060692B2 (en) 2010-10-12 2015-06-23 Pacesetter, Inc. Temperature sensor for a leadless cardiac pacemaker
US9687655B2 (en) 2010-10-12 2017-06-27 Pacesetter, Inc. Temperature sensor for a leadless cardiac pacemaker
US8543205B2 (en) 2010-10-12 2013-09-24 Nanostim, Inc. Temperature sensor for a leadless cardiac pacemaker
US9020611B2 (en) 2010-10-13 2015-04-28 Pacesetter, Inc. Leadless cardiac pacemaker with anti-unscrewing feature
US11890032B2 (en) 2010-12-13 2024-02-06 Pacesetter, Inc. Pacemaker retrieval systems and methods
US11786272B2 (en) 2010-12-13 2023-10-17 Pacesetter, Inc. Pacemaker retrieval systems and methods
US10188425B2 (en) 2010-12-13 2019-01-29 Pacesetter, Inc. Pacemaker retrieval systems and methods
US9126032B2 (en) 2010-12-13 2015-09-08 Pacesetter, Inc. Pacemaker retrieval systems and methods
US11759234B2 (en) 2010-12-13 2023-09-19 Pacesetter, Inc. Pacemaker retrieval systems and methods
US8615310B2 (en) 2010-12-13 2013-12-24 Pacesetter, Inc. Delivery catheter systems and methods
US9242102B2 (en) 2010-12-20 2016-01-26 Pacesetter, Inc. Leadless pacemaker with radial fixation mechanism
US9511236B2 (en) 2011-11-04 2016-12-06 Pacesetter, Inc. Leadless cardiac pacemaker with integral battery and redundant welds
US9802054B2 (en) 2012-08-01 2017-10-31 Pacesetter, Inc. Biostimulator circuit with flying cell
US10744332B2 (en) 2012-08-01 2020-08-18 Pacesetter, Inc. Biostimulator circuit with flying cell
US10850098B2 (en) 2014-03-24 2020-12-01 Bioness Inc. Systems and apparatus for gait modulation and methods of use
US9867985B2 (en) 2014-03-24 2018-01-16 Bioness Inc. Systems and apparatus for gait modulation and methods of use
US10086196B2 (en) 2014-03-24 2018-10-02 Bioness Inc. Systems and apparatus for gait modulation and methods of use
US11691009B2 (en) 2014-03-24 2023-07-04 Bioness Inc. Systems and apparatus for gait modulation and methods of use
US11724106B2 (en) 2016-01-11 2023-08-15 Bioness Inc. Systems and apparatus for gait modulation and methods of use
US11077300B2 (en) 2016-01-11 2021-08-03 Bioness Inc. Systems and apparatus for gait modulation and methods of use
US11235162B2 (en) 2017-11-29 2022-02-01 Medtronic, Inc. Tissue conduction communication between devices
US11660455B2 (en) 2017-11-29 2023-05-30 Medtronic, Inc. Tissue conduction communication using ramped drive signal
US11045654B2 (en) 2017-11-29 2021-06-29 Medtronic, Inc. Tissue conduction communication using ramped drive signal
US11213684B2 (en) 2017-11-29 2022-01-04 Medtronic, Inc. Device and method to reduce artifact from tissue conduction communication transmission
US11110279B2 (en) 2017-11-29 2021-09-07 Medtronic, Inc. Signal transmission optimization for tissue conduction communication
US11229796B2 (en) 2017-12-15 2022-01-25 Medtronic Inc. Device, system and method with adaptive timing for tissue conduction communication transmission

Also Published As

Publication number Publication date
US7513257B2 (en) 2009-04-07
US6564807B1 (en) 2003-05-20
US20050256551A1 (en) 2005-11-17
US6164284A (en) 2000-12-26

Similar Documents

Publication Publication Date Title
US6315721B2 (en) System of implantable devices for monitoring and/or affecting body parameters
US6564807B1 (en) System of implantable devices for monitoring and/or affecting body parameters
EP1011804B1 (en) System of implantable devices for monitoring and/or affecting body parameters
EP1702648B1 (en) System of implantable devices for monitoring and/or affecting body parameters
US8555894B2 (en) System for monitoring temperature
US7114502B2 (en) Battery-powered patient implantable device
US7450998B2 (en) Method of placing an implantable device proximate to neural/muscular tissue
US20050075682A1 (en) Neural device for sensing temperature
CA2281880C (en) Battery-powered patient implantable device
US6472991B1 (en) Multichannel communication protocol configured to extend the battery life of an implantable device
US7024249B2 (en) Pulsed magnetic control system for interlocking functions of battery powered living tissue stimulators
EP1508296A1 (en) A system for monitoring temperature

Legal Events

Date Code Title Description
AS Assignment

Owner name: ALFRED E. MANN FOUNDATION FOR SCIENTIFIC RESEARCH,

Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:SCHULMAN, JOSEPH H.;DELL, ROBERT DAN;GORD, JOHN C.;REEL/FRAME:019857/0853

Effective date: 19980325

STCB Information on status: application discontinuation

Free format text: ABANDONED -- FAILURE TO RESPOND TO AN OFFICE ACTION