CA2422636C - Acoustic switch and apparatus and methods for using acoustic switches within a body - Google Patents

Acoustic switch and apparatus and methods for using acoustic switches within a body Download PDF

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Publication number
CA2422636C
CA2422636C CA2422636A CA2422636A CA2422636C CA 2422636 C CA2422636 C CA 2422636C CA 2422636 A CA2422636 A CA 2422636A CA 2422636 A CA2422636 A CA 2422636A CA 2422636 C CA2422636 C CA 2422636C
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Prior art keywords
acoustic
implant
electrical circuit
switch
energy storage
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CA2422636A
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French (fr)
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CA2422636A1 (en
Inventor
Avraham Penner
Eyal Doron
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Remon Medical Technologies Ltd Israel
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Remon Medical Technologies Ltd Israel
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    • 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
    • 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
    • A61B5/0026Remote monitoring of patients using telemetry, e.g. transmission of vital signals via a communication network characterised by the transmission medium
    • A61B5/0028Body tissue as transmission medium, i.e. transmission systems where the medium is the human body
    • 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
    • A61B5/02Detecting, measuring or recording pulse, heart rate, blood pressure or blood flow; Combined pulse/heart-rate/blood pressure determination; Evaluating a cardiovascular condition not otherwise provided for, e.g. using combinations of techniques provided for in this group with electrocardiography or electroauscultation; Heart catheters for measuring blood pressure
    • A61B5/021Measuring pressure in heart or blood vessels
    • A61B5/0215Measuring pressure in heart or blood vessels by means inserted into the body
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00Measuring for diagnostic purposes; Identification of persons
    • A61B5/07Endoradiosondes
    • A61B5/076Permanent implantations
    • 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
    • A61B5/14539Measuring 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 pH
    • 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
    • A61N1/37217Means for communicating with stimulators characterised by the communication link, e.g. acoustic or tactile
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61NELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N5/00Radiation therapy
    • A61N5/06Radiation therapy using light
    • A61N5/0601Apparatus for use inside the body
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61NELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N5/00Radiation therapy
    • A61N5/06Radiation therapy using light
    • A61N5/0613Apparatus adapted for a specific treatment
    • A61N5/062Photodynamic therapy, i.e. excitation of an agent
    • 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
    • A61B2562/02Details of sensors specially adapted for in-vivo measurements
    • A61B2562/0247Pressure sensors
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B2562/00Details of sensors; Constructional details of sensor housings or probes; Accessories for sensors
    • A61B2562/02Details of sensors specially adapted for in-vivo measurements
    • A61B2562/028Microscale sensors, e.g. electromechanical sensors [MEMS]
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00Measuring for diagnostic purposes; Identification of persons
    • A61B5/01Measuring temperature of body parts ; Diagnostic temperature sensing, e.g. for malignant or inflamed tissue
    • AHUMAN NECESSITIES
    • A61MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61BDIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B5/00Measuring for diagnostic purposes; Identification of persons
    • A61B5/03Detecting, measuring or recording fluid pressure within the body other than blood pressure, e.g. cerebral pressure; Measuring pressure in body tissues or organs
    • A61B5/031Intracranial pressure
    • 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
    • A61NELECTROTHERAPY; MAGNETOTHERAPY; RADIATION THERAPY; ULTRASOUND THERAPY
    • A61N5/00Radiation therapy
    • A61N5/06Radiation therapy using light
    • A61N2005/065Light sources therefor
    • A61N2005/0651Diodes

Abstract

An implant for insertion or implantation within a body includes an electrical circuit for performing one or more commands when the implant is activated, an energy storage device, and a switch coupled to the electrical circuit and the energy storage device. An acoustic transducer is coupled to the switch, the acoustic transducer being activatable upon acoustic excitation by an external acoustic energy source for closing the switch to allow current flow from the energy storage device to the electrical circuit. The one or more commands includes measuring a physiological parameter with a biosensor coupled to the electrical circuit, or controlling a therapeutic device coupled to the electrical circuit. The therapeutic device or biosensor may be activated for a predetermined time or until the switch is opened in response to another acoustic excitation of the acoustic transducer.

Description

ACOUSTIC SWITCH AND APPARATUS AND METHODS FOR USING
ACOUSTIC SWITCHES WITHIN A BODY

INTRODUCTION
The present invention relates generally to devices for implantation within a patient's body, and more particularly to devices for activating, deactivating, and/or controlling implants located within a body that monitor physiological conditions and/or provide therapeutic functions.

BACKGROUND OF THE INVENTION
Devices are known that may be implanted within a patient's body to monitor one or more physiological conditions and/or to provide therapeutic functions.
For example, sensors or transducers may be located deep within the body for monitoring a variety of properties, such as temperature, pressure, strain, fluid flow, chemical properties, electrical properties, magnetic properties, and the like. In addition, devices may be implanted that perform one or more therapeutic functions, such as drug delivery, defibrillation, electrical stimulation, and the like.
Often it is desirable to control by external command such devices once they are implanted within a patient, for example, to obtain data, and/or to activate or otherwise control the implant. An implant may include wire leads from the implant to an exterior surface of the patient, thereby allowing an external controller or other device to be directly coupled to the implant. Alternatively, the implant may be remotely controlled, for example, using an external induction device. For example, an external radio frequency (RF) transmitter may be used to communicate with the implant. RF energy, however, may only penetrate a few millimeters into a body, because of the body's dielectric nature, and therefore may not be able to communicate effectively with an implant that is located deep within the body. In addition, although an RF transmitter may be able to induce a current within an implant, the implant's receiving antenna, generally a low impedance coil, may generate a voltage that is too low to provide a reliable switching mechanism.

In a further alternative, electromagnetic energy may be used to switch or otherwise control an implant, since a body generally does not attenuate magnetic Fields. The presence of external magnetic fields encountered by the patient during normal activity, however, may expose the patient to the risk of false positives, i.e., accidental activation or deactivation of the implant. Furthermore, external electromagnetic systems may be cumbersome and may not be able to effectively transfer coded information to an implant.

Accordingly, it is believed that a device that overcomes these problems and/or that may more effectively remotely activate or otherwise control an implant located within a patient's body may be considered useful.

SUMMARY OF THE INVENTION
The present invention, is generally directed to implants that may be surgically or otherwise located within a mammalian body for monitoring one or more physiological parameters and/or for performing one or more therapeutic functions. For example, an implant in accordance with the present invention may be used for atrial defibrillation, pain relief stimulation, neuro-stimulation, drug release, activation of a light source for photodynamic therapy, monitoring of a radiation dose including ionizing, magnetic or acoustic radiation, monitoring of flow in a bypass graft, producing cell oxygenation and membrane electroportation, and measurement of various physiological parameters including heart chamber pressure, infraction temperature, intracranial pressure, electrical impedance, position, orthopedic implant strain or pH.

2a According to one aspect of the present invention, there is provided an implant for surgical insertion, implantation, or location within a body, comprising: an electrical circuit configured for performing one or more commands when the implant is activated; a sensor coupled to the electrical circuit for measuring at least one physiological parameter within the body, the one or more commands comprising a command for activating the sensor; an energy storage device; a switch coupled to the electrical circuit and the energy storage device;
and an acoustic transducer coupled to the switch, the acoustic transducer being activatable upon acoustic excitation by an external acoustic energy source for actuating the switch between an open position, in which current is limited from flowing from the energy storage device to the electrical circuit, and a closed position, in which current flows from the energy storage device to the electrical circuit for activating the electrical circuit wherein, in the closed position, the acoustic transducer is configured to transmit an acoustic signal including the at least one sensed physiological parameter to a remote location.

According to another aspect of the present invention, there is provided a method for transmitting information to an implant comprising an acoustic switch coupled to an electrical circuit and an energy storage device, the implant being located within a body, the method comprising: transmitting one or more acoustic signals comprising an acoustic activation signal and an acoustic command signal from a source located outside of the body towards the implant, and closing the acoustic switch in response to the acoustic activation signal, whereupon current flows from the energy storage device to the electrical circuit;
wherein the acoustic switch sends an electrical command signal to the electrical circuit in response to the acoustic command signal.

In accordance with another aspect, an implement is provided that includes an electrical circuit configured for performing one or more commands when the implant is activated, an energy storage device, and a switch coupled to the electrical circuit and the energy storage device. An acoustic transducer is coupled to the switch that may be activated upon acoustic excitation by an external acoustic energy source for closing the switch to allow current flow from the energy storage device to the electrical circuit.

2b In one embodiment, the switch may be closed only when the acoustic transducer receives a first acoustic initiation signal followed by a second acoustic confirmation signal, the first and second acoustic signals being separated by a predetermined delay.
The switch may remain closed for a predetermined time and then automatically open.
Alternatively or in addition, the switch may be opened when an acoustic termination signal is received by the acoustic transducer for discontinuing current flow from the energy storage device to the electrical circuit.
In one preferred embodiment, the electrical circuit includes a sensor for measuring a physiological parameter within the body. A transmitter or the acoustic transducer itself may be coupled to the electrical circuit for receiving an electrical signal proportional to the physiological parameter measured by the sensor. The transmitter or acoustic transducer may transmit a signal including information regarding the physiological parameter to a receiver located outside the body. Preferably, the sensor is a biosensor configured for measuring at least one of blood pressure, heart chamber pressure, infraction temperature, intracranial pressure, electrical impedance, position, orthopedic implant strain, or pH, and the acoustic transducer enables communication of data from the sensor to a receiver located outside the body.
In another preferred embodiment, the electrical circuit includes an actuator for activating or controlling a therapeutic device within the body that is connected to or otherwise associated with the actuator. The electrical circuit may activate the therapeutic device for a predetermined time, or until the switch is opened. Alternatively, the electrical circuit may control the therapeutic device in response to a physiological parameter measured by a biosensor coupled to the electrical circuit.
During use, the acoustic transducer may receive a relatively low frequency acoustic signal that vibrates the piezoelectric layer at its resonant frequency. The acoustic signal closes the switch, activating the implant from its "sleep" mode to an "active"
mode. In the sleep mode, the implant may wait substantially indefinitely with substantially no energy consumption. Once activated, i.e., when the switch is closed, the electrical circuit performs one or more commands, such as measuring a physiological parameter within the body, or controlling a therapeutic device within the body. A signal proportional to the physiological parameter may be transmitted from the implant to a receiver located outside the body. Alternatively, the therapeutic device may be controlled based upon the physiological parameter.
In a further alternative, a set of command signals may be sent from a source outside the body along with or after the acoustic activation signal. The command signals may be interpreted by the electrical circuit to provide a set of commands to control the therapeutic device, e.g., to provide a desired course of treatment. For example, the commands may instruct the therapeutic device to provide a desired dosage for a desired duration, and/or may modify dosage or duration based upon feedback from the biosensor.
Other objects and features of the present invention will become apparent from consideration of the following description taken in conjunction with the accompanying drawings.

BRIEF DESCRIPTION OF THE DRAWINGS
The invention is herein described, by way of example only, with reference to the accompanying drawings, wherein:

FIGS. IA-IC are block diagrams, showing exemplary embodiments of an implant, in accordance with the present invention.

FIG. 2 is a schematic diagram, showing a preferred embodiment of an electrical switch circuit, in accordance with the present invention.

FIG. 3A is a cross-sectional view of an acoustic transducer element, in accordance with the present invention.

FIG. 3B is a cross-sectional view of the transducer element of FIG. 3A, taken along line B-B.

FIG. 3C is a cross sectional view of the transducer element of FIG. 3A, taken along line C-C.

FIG. 3D is a cross sectional view of the transducer element of FIG. 3A, taken along line D-D.

FIG. 3E is a cross sectional view of the transducer element of FIG. 3A, taken along line E-E.

FIG. 3F is a cross sectional view of the transducer element of FIG. 3A, taken along line F-F.

FIG. 3G is a cross sectional view of the transducer element of FIG. 3A, taken along line G-G.

FIG. 4 is a top view of a preferred embodiment of an electrode shaped for maximizing the power response of a transducer, in accordance with the present invention.

FIG. 5 is a cross-sectional view of another preferred embodiment of a transducer element, in accordance with the present invention.
5 FIG. 6A-6F are schematic views of exemplary embodiments of an acoustic transmitter that may be used as a transmitter, in accordance with the present invention.
FIG. 7 is a cross-sectional view of another preferred embodiment of a transmitter element, in accordance with the present invention.
FIG. S is a cross-sectional view of still another preferred embodiment of a transmitter element, in accordance with the present invention.

.DESCRIPTION OF THE PREFFERED EMBODIMENT
Turning to the drawings, FIGS. lA-IC schematically show several exemplary embodiments of an implant 110, 210, 310, in accordance with the present invention.
Generally, the implant 110, 210, 310 includes an electrical circuit 112, 212, configured for performing one or more functions or commands when the implant 110, 210, 310 is activated, as described further below. In addition, the implant 110, 210, 310 includes an energy storage device 114 and an acoustic switch 116 coupled to the electrical circuit 112, 212, 312 and the energy storage device 114. The acoustic switch 116 is preferably activated upon acoustic excitation 100 by an external acoustic energy source (not shown) to allow current flow from the energy storage device 114 to the electrical circuit 112, 212, 312. In a preferred embodiment, the acoustic switch 116 includes an acoustic transducer 118, such as that disclosed in US Patent No 6,140,740.
In addition, the acoustic switch 116 also includes a switch 120, such as switch circuit 400 shown in FIG. 2 and described further below, although alternatively other switches, such as a miniature electromechanical switch and the like (not'shown) may be provided.

The energy storage device 114 may be any of a variety of known devices, such as an energy exchanger, a battery and/or a capacitor (not shown). Preferably, the energy storage device 1 14 is capable of storing electrical energy substantially indefinitely for as long as the acoustic switch 116 remains open, i.e., when the implant 110, 210, 3 10 is in a "sleep" mode. In addition, the energy storage device 114 may be capable of being charged from an external source, e.g., inductively, as will be appreciated by those skilled in the art. In a preferred embodiment, the energy storage device 114 includes both a capacitor and a primary, non-rechargeable battery. Alternatively, the energy storage device 114 may include a secondary, rechargeable battery and/or capacitor that may be energized before activation or use of the implant 110, 210, 310.
The implant 110, 210, 310 may be surgically or minimally invasively inserted within a human body in order to carry out a variety of monitoring and/or therapeutic functions. For example, the electrical circuit 112, 212, 312 may include a control circuit 122, 222, 322, a biosensor 124, 224, an actuator 226, 326, and/or a transmitter 128, as explained in more detail below. The implant 210, 310 may be configured for providing one or more therapeutic functions, for example, to activate and/or control a therapeutic device implanted within a patient's body, such as an atrial defibrillator, a pain relief stimulator, a neuro-stimulator, a drug delivery device, and/or a light source used for photodynamic therapy. Alternatively, the implant may be used to monitor a radiation dose including ionizing, magnetic and/or acoustic radiation, to monitor flow in a bypass graft, to produce cell oxygenation and membrane electroportation, and the like. In addition or alternatively, the implant 110 may be used to measure one or more physiological parameters within the patient's body, such as pressure, temperature, electrical impedance, position, strain, pH, and the like.
An implant in accordance with the present invention operates in one of two modes, a "sleep" or "passive" mode when the implant remains dormant and not in use, i.e., when the acoustic switch 116 is open, and an "active" mode, when the acoustic switch 116 is closed, and electrical energy is delivered from the energy storage device 114 to the electrical circuit 112, 212, 312. Because the acoustic switch 116 is open in the sleep mode, there is substantially no energy consumption from the energy storage device 114, and consequently, the implant may remain in the sleep mode virtually indefinitely, i.e., until activated. Thus, an implant in accordance with the present invention may be more energy efficient and, therefore, may require a relatively small energy storage device than implants that continuously draw at least a small amount of current in their "passive"
mode.
To activate the implant 110, 210, 310, one or more external acoustic energy waves or signals 100 are transmitted from an external source into the patient's body (not shown), e.g., generally towards the location of the implant 110, 210, 310 until the signal is received by the acoustic transducer 118. Upon excitation by the acoustic wave(s) 100, the acoustic transducer 118 produces an electrical output that is used to close, open, or otherwise activate the switch 120. Preferably, in order to achieve reliable switching, the acoustic transducer 118 is configured to generate a voltage of at least several tenths of a volt upon excitation that may be used as an activation signal to close the switch 120.
As a safety measure against false positives (either erroneous activations or deactivations), the acoustic switch 116 may be configured to close only upon receipt of an initiation signal followed by a confirmation signal. For example, the acoustic switch 116 may only acknowledge an activation signal that includes a first pulse followed by a second pulse separated by a predetermined delay. Use of a confirmation signal may be particularly important for certain applications, for example, to prevent unintentional release of drugs by a drug delivery implant.
In addition to an activation signal, the acoustic transducer 118 may be configured for generating a termination signal in response to a second acoustic excitation (which may the same or different than the acoustic wave(s) used to activate the acoustic switch 116) in order to return the implant 110, 210, 310 to its sleep mode. For example, once activated, the switch 120 may remain closed indefinitely, e.g., until the energy storage device 114 is depleted or until a termination signal is received by the acoustic transducer 118. Alternatively, the acoustic switch 116 may include a timer (not shown), such that the switch 120 remains closed only for a predetermined time, whereupon the switch 120 may automatically open, returning the implant 110, 210, 310 to its sleep mode.
Turning to FIG. 1 A, a first preferred embodiment of an implant 110 is shown in which the electrical circuit 112 includes a controller 122, a biosensor 124 coupled to the controller 122, and a transmitter 128 coupled to the controller 122. The controller 122 may include circuitry for activating or controlling the biosensor 124, for receiving signals from the biosensor 124, and/or for processing the signals into data, for example, to be transmitted by the transmitter 128. Optionally, the electrical circuit 112 may include memory (not shown) for storing the data. The transmitter 128 may be any device capable of transmitting data from the controller 122 to a remote location outside the body, such as an acoustic transmitter, a radio frequency transmitter, and the like. In an alternative embodiment, the controller 122 may be coupled to the acoustic transducer 118 such that the acoustic transducer 118 may be used as a transmitter 128 instead of providing a separate transmitter.
The biosensor 124 may include one or more sensors capable of measuring physiological parameters, such as those described above. For example, U.S.
Patent Nos.
4,793,825 issued in the name of Benjamin et al. and 5,833,603 issued in the name of Kovacs et at. disclose exemplary embodiments of biosensors that may be included in an implant, in accordance with the present invention. The disclosure of these references and others cited therein are expressly incorporated herein by reference. Thus, the biosensor 124 may generate a signal proportional to a physiological parameter that may be processed and/or relayed by the controller 122 to the transmitter 128, which may, in turn, generate a transmission signal to be received by a device outside the patient's body. Data regarding the physiological parameter(s) may be transmitted continuously or periodically untiI the acoustic switch 116 is deactivated, or for a fixed predetermined time, as will be appreciated by those skilled in the art.
Turning to FIG. 113, a second preferred embodiment of an implant 210 is shown in which the electrical circuit 212 includes a controller 222 and an actuator 226. The actuator 226 may be coupled to a therapeutic device (not shown) provided in or otherwise coupled to the implant 210, such as a light source, a nerve stimulator, a defibrillator, or a valve communicating with an implanted drug reservoir (in the implant or otherwise implanted within the body in association with the implant). For example, the actuator 226 may be a light source for photo-dynamic therapy, such as that disclosed in U.S.
Patent No. 5,800,478 issued in the name of Chen et al.

When the switch 120 is closed, the controller 222 may activate the actuator using a pre-programmed protocol, e.g., to complete a predetermined therapeutic procedure, whereupon the switch 120 may automatically open, or the controller 222 may follow a continuous or looped protocol until the switch 120 is deactivated.
Alternatively, the acoustic transducer 118 may be coupled to the controller 222 for communicating a new or unique set of commands to the controller 222. For example, a particular course of treatment for a patient having the implant 210 may be determined, such as a now rate and duration of drug delivery or an energy level and duration of electrical stimulation.
Acoustic signals including commands specifying this course of treatment may be transmitted from an external device (not shown) to the acoustic switch 116, e.g., along with or subsequent to the activation signal 1,00. The controller 222 may interpret these commands and control the actuator 226 accordingly to complete the course of treatment.
Turning to FIG. 1C, yet another preferred embodiment of an implant 310 is shown in which the electrical circuit 312 includes a controller 322, a biosensor 324, and an actuator 326, all of which may be coupled to one another. This embodiment may operate similarly to the embodiments described above, e.g., to obtain data regarding one or more physiological parameters and/or to control a therapeutic device. In addition, once activated, the controller 322 may control the actuator 326 in response to data obtained from the biosensor 324 to automatically control, or adjust a course of treatment being provided by a device connected to the actuator 326. For example, the actuator 326 may be coupled to an insulin pump (not shown), and the biosensor 324 may measure glucose levels within the patient's body. The controller 322 may control the actuator to open or close a valve on the insulin pump to adjust a rate of insulin delivery based upon glucose levels measured by the biosensor 324 in order to maintain the patient's glucose within a desired range.

Turning to FIG. 2, a preferred embodiment of a switch 400 is shown that may be incorporated into an implant in accordance with the present invention. The switch 400 includes a piezoelectric transducer, or other acoustic transducer (not shown, but generally connected to the switch 400 at locations piezo + and piezo -), a plurality of MOSFET
transistors (Ql-Q4) and resistors (R1-R4), and switch S1. A "load" may be coupled to the switch 400, such as one of the electrical circuits described above. In the switch's "sleep" mode, all of the MOSFET transistors (Ql-Q4) are in an off state. To maintain the off state, the gates of the transistors are biased by pull-up and pull-down resistors.
The gates of N-channel transistors (Q1, Q3 & Q4) are biased to ground and the gate of P-channel transistor Q2 is biased to +3V. During this quiescent stage, switch Si is closed and no current flows through the circuit. Therefore, although an energy storage device (not shown, but coupled between the hot post, labeled with an exemplary voltage of +3V, and ground) is connected to the switch 400, no current is being drawn therefrom since all of the transistors are quiescent.

When the piezoelectric transducer detects an external acoustic signal, e.g., having 5 a particular frequency such as the transducer's resonant frequency, the voltage on the transistor Q1 will exceed the transistor threshold voltage of about one half of a volt.
Transistor Q1 is thereby switched on and current flows through transistor Q1 and pull-up resistor R2. As a result of the current flow through transistor Q1, the voltage on the drain of transistor Q1 and the gate of transistor Q2 drops from +3V substantially to zero 10 (ground). This drop in voltage switches on the P-channel transistor Q2, which begins to conduct through transistor Q2 and pull-down resistor R3.

As a result of the current flowing through transistor Q2, the voltage on the drain of transistor Q2 and the gates of transistors Q3 and Q4 increases from substantially zero to +3V. The increase in voltage switches on transistors Q3 and Q4. As a result, transistor Q3 begins to conduct through resistor R4 and main switching transistor Q4 begins to conduct through the "load," thereby switching on the electrical circuit.
As a result of the current flowing through transistor Q3, the gate of transistor Q2 is connected to ground through transistor Q3, irrespective of whether or not transistor Q1 is conducting. At this stage, the transistors (Q2, Q3 & Q4) are latched to the conducting state, even if the piezoelectric voltage on transistor Q1 is subsequently reduced to zero and transistor Q1 ceases to conduct. Thus, main switching transistor Q4 will remain on until switch S1 is opened.

In order to deactivate or open the switch 400, switch S1 must be opened, for example, while there is no acoustic excitation of the piezoelectric transducer. If this occurs, the gate of transistor Q2 increases to +3V due to pull-up resistor R2.
Transistor Q2 then switches off, thereby, in turn, switching off transistors Q3 and Q4.
At this stage, the switch 400 returns to its sleep mode, even if switch S 1 is again closed.
The switch 400 will only return to its active mode upon receiving a new acoustic activation signal from the piezoelectric transducer.

It should be apparent to one of ordinary skill in the art that the above-mentioned electrical circuit is not the only possible implementation of a switch for use with the present invention. For example, the switching operation my be performed using a CMOS
circuit, which may draw less current when switched on, an electromechanical switch, and the like.

Turning to FIGS. 3A-3G, a preferred embodiment of an acoustic transducer 1 is shown that includes a miniature flexural acoustic transducer capable of receiving external acoustic signals and producing an electrical output to "activate," i.e., deliver electrical current in or to an electrical circuit. Preferably, as explained above with respect to FIGS.
I A-I C, the electrical output from the acoustic transducer 118 is used to open and/or close the switch 120, allowing current flow in one or more the components of the electrical circuit 112, 212, 312. In addition, the electrical output from the acoustic transducer 118 may be transferred via a communications bus to other components of the implant 110, for example, to provide commands to a control circuit or internal processor.

In a preferred embodiment, the acoustic transducer I is configured for receiving relatively low frequency acoustic signals (up to several megahertz) for vibrating a piezoelectric layer 2 in the acoustic transducer I at its resonant frequency.
Preferably, the acoustic transducer 1 may respond to acoustic excitation signal between about kilohertz, and more preferably has a resonant frequency of about 40 kilohertz.
Unlike high frequency waves (those greater than several megahertz), low frequency acoustic waves are generally only slightly attenuated by water-based tissues within the body.
Consequently, low frequency acoustic waves may reach almost any point of the body, including deeply located organs, such as the heart, liver, or brain.

Returning to FIG. 3A, the transducer element 1 includes at least one cell member 3, including a cavity 4 etched into a substrate and covered by a substantially flexible piezoelectric layer 2. Preferably, the cavity 4 is etched into the substrate using conventional printed-circuit photolithography methods. Alternatively, the cavity 4 may be etched into the substrate using VLSI/micro-machining technology or any other suitable technology.

The cavity 4 preferably includes a gas, such as air, providing a predetermined pressure within the cavity 4 that may be selected to provide a desired sensitivity and ruggedness of the transducer, as well as to at least partially define the resonant frequency of the piezoelectric layer 2. An upper electrode 8 and a lower electrode 6 are attached to the piezoelectric layer 2, the electrodes 6, 8 being coupled to the switch 400, for example, at points Piezo + and Piezo -, as described above with reference to FIG. 2.
The substrate is preferably made of an electrical conducting layer 11 disposed on an electrically insulating layer 12, such that the cavity 4 is etched substantially through the thickness of electrically conducting layer 11.

The electrically conducting layer I 1 is preferably made of copper and the insulating layer 12 is preferably made of a polymer such as polyamide.
Conventional copper-plated polymer laminate such as KaptonTM sheets may be used for the production of the transducer element 1. Alternatively, commercially available laminates, such as NovacladTM, may be used. In a further alternative, the substrate may include a silicon layer, or any other suitable material, andlor the electrically conducting layer 11 may be made of a non-conductive material such as PyralinTM.

According to a preferred embodiment, the cavity 4 features a circular or hexagonal shape with radius of about 200 m. The electrically conducting layer preferably has a thickness of about 15 m. The cell member 3 is preferably etched completely through the thickness of the electrically conducting layer 11. The electrically insulating layer 12 preferably features a thickness of about 50 m. The piezoelectric layer 2 may be made of PVDF or a copolymer thereof Alternatively, piezoelectric layer 2 may be made of a substantially flexible piezoceramic. In a preferred embodiment, the piezoelectric layer 2 is a poled PVDF sheet having a thickness of about 9-28 m-As best seen in FIG. 3D, an insulating chamber 18 is etched into the substrate, preferably through the thickness of the conducting layer 11, so as to insulate the transducer element from other portions of the substrate that may include other electrical components, such as other transducer elements etched into the substrate.
According to a specific embodiment, the width of the insulating chamber 18 is about 100 m.
As shown, the insulating chamber 18 is etched into the substrate so as to form a wall 10 of a predetermined thickness enclosing the cavity 4, and a conducting line 17 is integrally made with the wall 10 for connecting the transducer element to another electronic component preferably etched into the same substrate, or to an external electronic circuit (not shown). The upper electrode 8 and lower electrode 6 are preferably precisely shaped so as to cover a predetermined area of the piezoelectric layer 2. The electrodes 6, 8 may be deposited on the upper and lower surfaces of the piezoelectric membrane 2, respectively, by using various methods such as vacuum deposition, mask etching, painting, and the like.

As shown in FIG. 3B, the lower electrode 6 is preferably made as an integral part of a substantially thin electrically conducting layer 14 disposed on electrically conducting layer 11. Preferably, electrically conducting layer 14 is made of a Nickel-Copper alloy and is attached to the electrically conducting layer 11 by means of a sealing connection 16, which may be made of indium. According to a preferred embodiment, the sealing connection 16 may feature a thickness of about 10 m, such that the overall height of wall 10 of cavity 4 is about 20-25 m.
It will be appreciated that the precise dimensions of the various elements of a transducer element in accordance with the present invention may be specifically tailored according to the requirements of the specific application, and should not be limited to the exemplary dimensions provided herein. For example, the thickness and radius of the piezoelectric layer 2, as well as the pressure within cavity 4, may be specifically selected so as to provide a predetermined resonant frequency.
By using a substantially flexible piezoelectric layer 2, a miniature transducer element is provided that has a resonant frequency having an acoustic wavelength that is much larger than the extent of the transducer. This enables the transducer to be omnidirectional even at resonance, and further allows the use of relatively low frequency acoustic signals that do not suffer from significant attenuation in the surrounding medium. Thus, the transducer element may be suitable for application in confined or hidden locations where the orientation of the transducer element may not be ascertained in advance.
Returning to FIGS. 3A, 3B, and 3E, the electrically conducting layer 14 covers the various portions of the conducting layer 11, including wall 10 and conducting line 17.
The portion of the conducting layer 14 covering the conducting line 17 may be used for connection to an electronic component, such as a neighboring cell.
According to a preferred embodiment, the electrodes 6, 8 are specifically shaped to include the most energy-productive region of the piezoelectric layer 2 so as to provide maximal response of the transducer while optimizing the electrode area, and therefore the cell capacitance, thereby maximizing a selected parameter such as voltage sensitivity, current sensitivity, or power sensitivity of the transducer element. Turning to FIG. 4, a preferred electrode shape for maximizing the power response of the transducer is shown in which the electrode includes two electrode portions 80a and 80b substantially covering the maximal charge density portions of layer 2, the electrode portions being interconnected by means of a connecting member 82 having a minimal area.
Preferably, the electrode portions 80a and 80b cover the portions of piezoelectric layer 2 that yield at least a selected threshold (e.g. 30%) of the maximal charge density.
According to the present invention any other parameter may be optimized so as to determine the shape of electrodes 6 and 8. According to further features of the present invention, only one electrode (either the upper electrode 8 or lower electrode 6) may be shaped so as to provide maximal electrical response of the transducer, with the other electrode covering the entire area of the piezoelectric layer 2. Since the charge is collected only at the portions of the piezoelectric layer 2 received between the upper and lower electrodes 8, 6, this configuration may be operatively equivalent to a configuration including two shaped electrodes having identical shapes.
Turning to FIG. 5, another preferred embodiment of a acoustic transducer is shown, including a transducer element I over a chamber 4 that may contain gas at a substantially low pressure, thereby conferring a substantially concave shape to the piezoelectric membrane 2 at equilibrium. This configuration may enhance the electrical response of the transducer by increasing the total charge obtained for a given displacement of layer 2. For example, this embodiment may increase the charge output of the piezoelectric layer 2 for a given displacement, thereby increasing the voltage, current and power responses of the transducer without having to increase the acoustic pressure. Further, it may further facilitate miniaturization of the transducer since the same electrical response may be obtained for smaller acoustic deflections.
This transducer may also be substantially more robust mechanically and therefore more durable than the first embodiment described above with respect to FIGS. 3A-3G.
This further miniaturization may also allow higher resonance frequencies relative to the embodiment shown of FIGS. 3A-3G.

An acoustic transducer element according to the present invention may also be used as a transmitter, for example, for transmitting information from an implant to a remote receiver, e.g., by modulating the reflection of an external impinging acoustic wave arrived from a remote transmitter. The transducer element generally functions as a 5 transmitter element due to the asymmetric fluctuations of the piezoelectric layer with respect to positive and negative transient acoustic pressures obtained as a result of the pressure differential between the interior and exterior of the underlying cavity.
The transmitter element preferably modulates the reflection of an external impinging acoustic wave by means of a switching element connected thereto, e.g., in the 10 electrical circuit of an implant as described above. The switching element may encode the information that is to be transmitted, such as the output of a sensor, thereby frequency modulating a reflected acoustic wave. This may require very little expenditure of energy from the transmitting module itself, since the acoustic wave that is received is externally generated, such that the only energy required for transmission is the energy of 15 modulation. Specifically, the reflected acoustic signal is modulated by switching the switching element according to the frequency of a message electric signal arriving from another electronic component such as a sensor, so as to controllably change the mechanical impedance of the piezoelectric layer according to the frequency of the message signal. Preferably, the invention uses a specific array of electrodes connected to a single cell member or alternatively to a plurality of cell members so as to control the mechanical impedance of the piezoelectric layer.
FIGS. 6A-6F show exemplary configurations of a transducer element including a piezoelectric layer 2 that may be controllably changed to provide a transmitter.
Referring to FIG. 6A, the transmitter element may include a first and second pairs of electrodes, the first pair including an upper electrode 40a and a lower electrode 38a, and the second pair including an upper electrode 40b and a lower electrode 38b.
Electrodes 38a, 38b, 40a and 40b are electrically connected to an electrical circuit (not shown) by means of conducting lines 36a, 36b, 34a and 34b, respectively, the electrical circuit including a switching element (also not shown) so as to alternately change the electrical connections of the conducting lines 36a, 36b, 34a and 34b.
Preferably, the switching element switches between a parallel connection and an anti-parallel connection of the electrodes. A parallel connection decreases the mechanical impedance of the piezoelectric layer 2, and an anti-parallel connection increases the mechanical impedance of the piezoelectric layer 2. An anti-parallel connection may be obtained by interconnecting line 34a to 36b and line 34b to 36a. A parallel connection may be obtained by connecting line 34a to 34b and line 36a to 36b. Preferably, the switching frequency equals the frequency of a message signal arriving from an electrical component such as a sensor.
According to another embodiment, shown in FIG. 6B, upper electrode 40a is connected to lower electrode 38b by means of a conducting line 28, and electrodes 38a and 40b are connected to an electrical circuit by means of conducting lines 27 and 29, respectively, the electrical circuit including a switching element. This embodiment provides an anti-parallel connection of the electrodes such that the switching element functions as an on/off switch, thereby alternately increasing the mechanical impedance of the piezoelectric layer 2.
In order to reduce the complexity of the electrical connections, the piezoelectric layer 2 may be depolarized and then repolarized at specific regions thereof.
As shown in FIG. 6C, the polarity of the portion of the piezoelectric layer 2 received between the electrodes 40a and 38a is opposite to the polarity of the portion of the piezoelectric layer 2 received between the electrodes 40b and 38b. An anti-parallel connection is thus achieved by interconnecting the electrodes 38a and 38b by means of a conducting line 28, and providing conducting lines 27 and 29 connected to the electrodes 40a and 40b, respectively, the conducting lines for connection to an electrical circuit including a switching element.
Turning to 6D, another embodiment is shown in which the transmitting element includes a plurality of transducing cell members, such that the mechanical impedance of piezoelectric layer 2 is controllably changed by appropriately interconnecting the cell members. A first transducing cell member 3a includes a layer 2a and a cavity 4a, and a second transducing cell member 3b includes a layer 2b and a cavity 4b that are preferably contained within the same substrate. A first pair of electrodes including electrodes 6a and 8a is attached to the piezoelectric layer 2, and a second pair of electrode including electrodes 6b and 8b is attached to the piezoelectric layer 2b. The electrodes 6a, 8a, 6b and 8b are electrically connected to an electrical circuit (not shown) by means of conducting lines 37a, 35a, 37b and 35b, respectively, the electrical circuit including a switching element so as to alternately switch the electrical connections of the conducting lines 37a, 35a, 37b and 35b so as to alternately provide parallel and anti-parallel connections, substantially as described for FIG. 6A, thereby alternately decreasing and increasing the mechanical impedance of the piezoelectric layers 2a and 2b.

FIG. 8E shows another embodiment in which the first and second transducing cell members are interconnected by means of an anti-parallel connection. As shown, the polarity of piezoelectric layer 2a is opposite to the polarity of layer 2b so as to reduce the complexity of the electrical connections between cell members 3a and 3b. Thus, electrode 6a is connected to electrode 6b by means of a conducting line 21, and electrodes 8a and 8b are provided with conducting lines 20 and 22, respectively, for connection to an electrical circuit including a switching element (not shown), wherein the switching element preferably functions as an on/off switch that alternately increases the mechanical impedance of the piezoelectric layers 2a and 2b.
FIG.6 F shows another embodiment in which the first and second transducing cell members are interconnected by means of a parallel connection. As shown, electrodes 6a and 6b are interconnected by means of conducting line 24, electrodes 8a and 8b are interconnected by means of conducting line 23, and electrodes 6b and 8b are provided with conducting lines 26 and 25, respectively, the conducting lines for connection to an electrical circuit including a switching element. The switching element preferably functions as an on/off switch for alternately decreasing and increasing the mechanical impedance of layers 2a and 2b.

FIG. 7 shows a possible configuration of two transducing cell members etched onto the same substrate and interconnected by means of an anti-parallel connection. As shown, the transducing cell members are covered by a common piezoelectric layer 2, wherein the polarity of the portion of the piezoelectric layer 2 received between electrodes 6a and 8a is opposite to the polarity of the portion of the piezoelectric layer 2 received between electrodes 6b and 8b. The electrodes 8a and 8b are bonded by means of a conducting line 9, and the electrodes 6a and 6b are provided with conducting lines 16 for connection to an electrical circuit (not shown).

Yet another embodiment of a transmitter element according to the present invention is shown in FIG. 8. The transmitter element includes a transducing cell member having a cavity 4 covered by a first and second piezoelectric layers 50a, 50b, preferably having opposite polarities. Preferably, the piezoelectric layers 50a, 50b are interconnected by means of an insulating layer 52. Upper and lower electrodes 44a, 42a are attached to the piezoelectric layer SOa, and upper and lower electrodes 44b and 42b are attached to the piezoelectric layer 50b. The electrodes 44a, 42a, 44b and 42b are provided with conducting lines 54, 55, 56 and 57, respectively, for connection to an electrical circuit.

It will be appreciated that the above descriptions are intended only to serve as examples, and that many other embodiments are possible within the spirit and the scope of the present invention.

Claims (25)

CLAIMS:
1. An implant for surgical insertion, implantation, or location within a body, comprising:

an electrical circuit configured for performing one or more commands when the implant is activated;

a sensor coupled to the electrical circuit for measuring at least one physiological parameter within the body, the one or more commands comprising a command for activating the sensor;

an energy storage device;

a switch coupled to the electrical circuit and the energy storage device; and an acoustic transducer coupled to the switch, the acoustic transducer being activatable upon acoustic excitation by an external acoustic energy source for actuating the switch between an open position, in which current is limited from flowing from the energy storage device to the electrical circuit, and a closed position, in which current flows from the energy storage device to the electrical circuit for activating the electrical circuit wherein, in the closed position, the acoustic transducer is configured to transmit an acoustic signal including the at least one sensed physiological parameter to a remote location.
2. The implant of claim 1, wherein the switch is configured such that the switch is closed only when the acoustic transducer receives a first acoustic excitation signal followed by a second acoustic excitation signal, the first and second acoustic excitation signals being separated by a predetermined delay.
3. The implant of claim 1, wherein the acoustic transducer is configured for receiving a first acoustic excitation signal and a second acoustic excitation signal, the switch being closed when the first acoustic excitation signal is received by the acoustic transducer, and the switch being opened when the second acoustic excitation signal is received by the acoustic transducer for discontinuing current flow from the energy storage device to the electrical circuit.
4. The implant of claim 1, wherein the acoustic transducer is configured for receiving a first acoustic excitation signal followed by a second acoustic excitation signal, the electrical circuit configured for interpreting the second acoustic excitation signal as one of a predetermined set of commands.
5. The implant of any one of claims 1 to 4, wherein the electrical circuit comprises a transmitter for transmitting a signal proportional to the physiological parameter to a receiver located outside the body.
6. The implant of any one of claims 1 to 4, wherein the acoustic transducer is coupled to the electrical circuit, and wherein the acoustic transducer is configured for transmitting a signal proportional to the physiological parameter to a receiver external to the body.
7. The implant of any one of claims 1 to 6, further comprising a therapeutic device coupled to the electrical circuit, the electrical circuit being configured for controlling the therapeutic device in response to the physiological parameter measured by the sensor.
8. The implant of any one of claims 1 to 7, wherein the one or more commands comprises activating an actuator coupled to the electrical circuit, the actuator being configured for controlling a therapeutic device coupled to the actuator.
9. The implant of any one of claims 1 to 8, wherein the acoustic transducer comprises:

a cell member having a cavity;

a substantially flexible piezoelectric layer attached to the cell member, the piezoelectric layer having an external surface and an internal surface, the piezoelectric layer having predetermined dimensions for enabling fluctuations at its resonance frequency upon impinging of an external acoustic wave; and a first electrode attached to the external surface and a second electrode attached to the internal surface.
10. The implant of any one of claims 1 to 9, wherein the energy storage device comprises a battery.
11. The implant of any one of claims 1 to 10, wherein the energy storage device comprises a rechargeable device, the rechargeable device being rechargeable by a device external to the body.
12. The implant of any one of claims 1 to 11, further comprising a timer coupled to the switch, the timer configured for opening the switch after a predetermined time has passed after the switch is initially closed.
13. A method for transmitting information to an implant comprising an acoustic switch coupled to an electrical circuit and an energy storage device, the implant being located within a body, the method comprising:

transmitting one or more acoustic signals comprising an acoustic activation signal and an acoustic command signal from a source located outside of the body towards the implant, and closing the acoustic switch in response to the acoustic activation signal, whereupon current flows from the energy storage device to the electrical circuit;

wherein the acoustic switch sends an electrical command signal to the electrical circuit in response to the acoustic command signal.
14. The method of claim 13, wherein the electrical circuit performs one or more commands when the switch is closed.
15. The method of claim 14, wherein the one or more commands comprises measuring a physiological parameter within the body.
16. The method of claim 15, further comprising transmitting a signal proportional to the physiological parameter from the implant to a receiver located outside the body.
17. The method of claim 15 or 16, wherein the one or more commands comprises controlling a therapeutic device within the body in response to the physiological parameter.
18. The method of any one of claims 13 to 17, wherein the acoustic switch remains closed until the energy storage device is depleted.
19. The method of any one of claims 13 to 17, wherein the acoustic switch automatically opens after a predetermined time to discontinue current flow from the energy storage device to the electrical circuit.
20. The method of any one of claims 13 to 17, further comprising transmitting an acoustic termination signal from a source located outside of the body towards the implant, the acoustic switch opening in response to the acoustic termination signal to discontinue current flow from the energy storage device to the electrical circuit.
21. The method of any one of claims 13 to 17, wherein the acoustic activation signal comprises a first acoustic excitation signal and a second acoustic excitation signal separated by a predetermined delay.
22. The method of claim 13, comprising transmitting the acoustic command signal from the source outside the body to the implant following the acoustic activation signal.
23. The method of any one of claims 13, 14 or 22, wherein the electrical circuit interprets the electrical command signal to perform one or more pre-defined commands.
24. The method of any one of claims 13, 14 or 22, wherein the electrical circuit performs one of a plurality of known commands in response to the electrical command signal.
25. The method of any one of claims 13 to 24, further comprising charging the energy storage device with an energy source located outside the body before transmitting the acoustic activation signal.
CA2422636A 2000-10-16 2001-10-15 Acoustic switch and apparatus and methods for using acoustic switches within a body Expired - Fee Related CA2422636C (en)

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PCT/IL2001/000951 WO2002032502A1 (en) 2000-10-16 2001-10-15 Acoustic switch and apparatus and methods for using acoustic switches within a body

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Families Citing this family (193)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20030036746A1 (en) 2001-08-16 2003-02-20 Avi Penner Devices for intrabody delivery of molecules and systems and methods utilizing same
US7283874B2 (en) 2000-10-16 2007-10-16 Remon Medical Technologies Ltd. Acoustically powered implantable stimulating device
US7024248B2 (en) * 2000-10-16 2006-04-04 Remon Medical Technologies Ltd Systems and methods for communicating with implantable devices
US7198603B2 (en) 2003-04-14 2007-04-03 Remon Medical Technologies, Inc. Apparatus and methods using acoustic telemetry for intrabody communications
US6764446B2 (en) 2000-10-16 2004-07-20 Remon Medical Technologies Ltd Implantable pressure sensors and methods for making and using them
US7727221B2 (en) * 2001-06-27 2010-06-01 Cardiac Pacemakers Inc. Method and device for electrochemical formation of therapeutic species in vivo
US20040122294A1 (en) 2002-12-18 2004-06-24 John Hatlestad Advanced patient management with environmental data
US20040122487A1 (en) 2002-12-18 2004-06-24 John Hatlestad Advanced patient management with composite parameter indices
US7043305B2 (en) 2002-03-06 2006-05-09 Cardiac Pacemakers, Inc. Method and apparatus for establishing context among events and optimizing implanted medical device performance
US8391989B2 (en) 2002-12-18 2013-03-05 Cardiac Pacemakers, Inc. Advanced patient management for defining, identifying and using predetermined health-related events
US8043213B2 (en) 2002-12-18 2011-10-25 Cardiac Pacemakers, Inc. Advanced patient management for triaging health-related data using color codes
US7983759B2 (en) 2002-12-18 2011-07-19 Cardiac Pacemakers, Inc. Advanced patient management for reporting multiple health-related parameters
US8712549B2 (en) 2002-12-11 2014-04-29 Proteus Digital Health, Inc. Method and system for monitoring and treating hemodynamic parameters
US7378955B2 (en) * 2003-01-03 2008-05-27 Cardiac Pacemakers, Inc. System and method for correlating biometric trends with a related temporal event
US7200439B2 (en) 2003-01-24 2007-04-03 Proteus Biomedical, Inc. Method and apparatus for enhancing cardiac pacing
US7267649B2 (en) * 2003-01-24 2007-09-11 Proteus Biomedical, Inc. Method and system for remote hemodynamic monitoring
EP1585441A4 (en) * 2003-01-24 2008-05-21 Proteus Biomedical Inc Methods and systems for measuring cardiac parameters
WO2005004754A2 (en) * 2003-06-30 2005-01-20 Js Vascular, Inc. Subcutaneous implantable non-thrombogenic mechanical devices
US7572228B2 (en) 2004-01-13 2009-08-11 Remon Medical Technologies Ltd Devices for fixing a sensor in a lumen
US7471986B2 (en) * 2004-02-20 2008-12-30 Cardiac Pacemakers, Inc. System and method for transmitting energy to and establishing a communications network with one or more implanted devices
US7765001B2 (en) 2005-08-31 2010-07-27 Ebr Systems, Inc. Methods and systems for heart failure prevention and treatments using ultrasound and leadless implantable devices
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
US7489967B2 (en) * 2004-07-09 2009-02-10 Cardiac Pacemakers, Inc. Method and apparatus of acoustic communication for implantable medical device
WO2006029090A2 (en) * 2004-09-02 2006-03-16 Proteus Biomedical, Inc. Methods and apparatus for tissue activation and monitoring
US20060064142A1 (en) * 2004-09-17 2006-03-23 Cardiac Pacemakers, Inc. Systems and methods for deriving relative physiologic measurements using an implanted sensor device
US20060064134A1 (en) * 2004-09-17 2006-03-23 Cardiac Pacemakers, Inc. Systems and methods for deriving relative physiologic measurements
US7813808B1 (en) 2004-11-24 2010-10-12 Remon Medical Technologies Ltd Implanted sensor system with optimized operational and sensing parameters
ATE484232T1 (en) 2004-11-24 2010-10-15 Remon Medical Technologies Ltd IMPLANTABLE MEDICAL DEVICE WITH INTEGRATED ACOUSTIC TRANSDUCER
US7384403B2 (en) * 2004-12-17 2008-06-10 Depuy Products, Inc. Wireless communication system for transmitting information from a medical device
EP1835964B1 (en) * 2004-12-21 2016-03-09 EBR Systems, Inc. Leadless cardiac system for pacing and arrhythmia treatment
US7606621B2 (en) * 2004-12-21 2009-10-20 Ebr Systems, Inc. Implantable transducer devices
US7558631B2 (en) * 2004-12-21 2009-07-07 Ebr Systems, Inc. Leadless tissue stimulation systems and methods
US8001975B2 (en) * 2004-12-29 2011-08-23 Depuy Products, Inc. Medical device communications network
US10390714B2 (en) 2005-01-12 2019-08-27 Remon Medical Technologies, Ltd. Devices for fixing a sensor in a lumen
US7545272B2 (en) 2005-02-08 2009-06-09 Therasense, Inc. RF tag on test strips, test strip vials and boxes
US8036743B2 (en) 2005-03-31 2011-10-11 Proteus Biomedical, Inc. Automated optimization of multi-electrode pacing for cardiac resynchronization
US20070007285A1 (en) * 2005-03-31 2007-01-11 Mingui Sun Energy delivery method and apparatus using volume conduction for medical applications
DE102005014573A1 (en) * 2005-03-31 2006-10-12 Stryker Trauma Gmbh Data transmission system in connection with an implant
US9339650B2 (en) 2005-04-13 2016-05-17 The Cleveland Clinic Foundation Systems and methods for neuromodulation using pre-recorded waveforms
US7715912B2 (en) * 2005-04-13 2010-05-11 Intelect Medical, Inc. System and method for providing a waveform for stimulating biological tissue
WO2006113397A2 (en) * 2005-04-13 2006-10-26 Nagi Hatoum System and method for providing a waveform for stimulating biological tissue
WO2007021804A2 (en) 2005-08-12 2007-02-22 Proteus Biomedical, Inc. Evaluation of depolarization wave conduction velocity
US7742815B2 (en) 2005-09-09 2010-06-22 Cardiac Pacemakers, Inc. Using implanted sensors for feedback control of implanted medical devices
US8649875B2 (en) 2005-09-10 2014-02-11 Artann Laboratories Inc. Systems for remote generation of electrical signal in tissue based on time-reversal acoustics
US7702392B2 (en) 2005-09-12 2010-04-20 Ebr Systems, Inc. Methods and apparatus for determining cardiac stimulation sites using hemodynamic data
US8273071B2 (en) 2006-01-18 2012-09-25 The Invention Science Fund I, Llc Remote controller for substance delivery system
US9254256B2 (en) 2005-11-09 2016-02-09 The Invention Science Fund I, Llc Remote controlled in vivo reaction method
US9028467B2 (en) 2005-11-09 2015-05-12 The Invention Science Fund I, Llc Osmotic pump with remotely controlled osmotic pressure generation
US20070106271A1 (en) 2005-11-09 2007-05-10 Searete Llc, A Limited Liability Corporation Remote control of substance delivery system
US9067047B2 (en) 2005-11-09 2015-06-30 The Invention Science Fund I, Llc Injectable controlled release fluid delivery system
GB2446096B (en) * 2005-11-09 2012-01-11 Searete Llc Accoustically controlled reaction device
US8992511B2 (en) * 2005-11-09 2015-03-31 The Invention Science Fund I, Llc Acoustically controlled substance delivery device
US8936590B2 (en) 2005-11-09 2015-01-20 The Invention Science Fund I, Llc Acoustically controlled reaction device
US8083710B2 (en) * 2006-03-09 2011-12-27 The Invention Science Fund I, Llc Acoustically controlled substance delivery device
US8060214B2 (en) 2006-01-05 2011-11-15 Cardiac Pacemakers, Inc. Implantable medical device with inductive coil configurable for mechanical fixation
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
US8089029B2 (en) 2006-02-01 2012-01-03 Boston Scientific Scimed, Inc. Bioabsorbable metal medical device and method of manufacture
US7328131B2 (en) * 2006-02-01 2008-02-05 Medtronic, Inc. Implantable pedometer
US8016859B2 (en) 2006-02-17 2011-09-13 Medtronic, Inc. Dynamic treatment system and method of use
US7993269B2 (en) * 2006-02-17 2011-08-09 Medtronic, Inc. Sensor and method for spinal monitoring
US20070208390A1 (en) * 2006-03-01 2007-09-06 Von Arx Jeffrey A Implantable wireless sound sensor
US20080140057A1 (en) 2006-03-09 2008-06-12 Searete Llc, A Limited Liability Corporation Of State Of The Delaware Injectable controlled release fluid delivery system
US8048150B2 (en) 2006-04-12 2011-11-01 Boston Scientific Scimed, Inc. Endoprosthesis having a fiber meshwork disposed thereon
US7744542B2 (en) * 2006-04-20 2010-06-29 Cardiac Pacemakers, Inc. Implanted air passage sensors
US7650185B2 (en) 2006-04-25 2010-01-19 Cardiac Pacemakers, Inc. System and method for walking an implantable medical device from a sleep state
US20080046038A1 (en) * 2006-06-26 2008-02-21 Hill Gerard J Local communications network for distributed sensing and therapy in biomedical applications
US7908334B2 (en) * 2006-07-21 2011-03-15 Cardiac Pacemakers, Inc. System and method for addressing implantable devices
US7912548B2 (en) 2006-07-21 2011-03-22 Cardiac Pacemakers, Inc. Resonant structures for implantable devices
US7955268B2 (en) 2006-07-21 2011-06-07 Cardiac Pacemakers, Inc. Multiple sensor deployment
EP2043740A2 (en) 2006-07-21 2009-04-08 Cardiac Pacemakers, Inc. Ultrasonic transducer for a metallic cavity implanted medical device
JP5155311B2 (en) * 2006-07-21 2013-03-06 カーディアック ペースメイカーズ, インコーポレイテッド Ultrasonic transmitting / receiving transducer housed in header of implantable medical device
CA2659761A1 (en) 2006-08-02 2008-02-07 Boston Scientific Scimed, Inc. Endoprosthesis with three-dimensional disintegration control
US8512241B2 (en) * 2006-09-06 2013-08-20 Innurvation, Inc. Methods and systems for acoustic data transmission
US20080071328A1 (en) * 2006-09-06 2008-03-20 Medtronic, Inc. Initiating medical system communications
EP2063766B1 (en) * 2006-09-06 2017-01-18 Innurvation, Inc. Ingestible low power sensor device and system for communicating with same
US8808726B2 (en) 2006-09-15 2014-08-19 Boston Scientific Scimed. Inc. Bioerodible endoprostheses and methods of making the same
CA2663271A1 (en) 2006-09-15 2008-03-20 Boston Scientific Limited 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
ES2368125T3 (en) 2006-09-15 2011-11-14 Boston Scientific Scimed, Inc. BIOEROSIONABLE ENDOPROOTHESIS WITH BIOESTABLE INORGANIC LAYERS.
US8676349B2 (en) 2006-09-15 2014-03-18 Cardiac Pacemakers, Inc. Mechanism for releasably engaging an implantable medical device for implantation
US8057399B2 (en) 2006-09-15 2011-11-15 Cardiac Pacemakers, Inc. Anchor for an implantable sensor
WO2008036548A2 (en) 2006-09-18 2008-03-27 Boston Scientific Limited Endoprostheses
EP2277563B1 (en) 2006-12-28 2014-06-25 Boston Scientific Limited Bioerodible endoprostheses and method of making the same
US8361023B2 (en) * 2007-02-15 2013-01-29 Baxter International Inc. Dialysis system with efficient battery back-up
US8622991B2 (en) 2007-03-19 2014-01-07 Insuline Medical Ltd. Method and device for drug delivery
US9220837B2 (en) 2007-03-19 2015-12-29 Insuline Medical Ltd. Method and device for drug delivery
MX2009010000A (en) 2007-03-19 2010-03-17 Insuline Medical Ltd Drug delivery device.
WO2009081262A1 (en) 2007-12-18 2009-07-02 Insuline Medical Ltd. Drug delivery device with sensor for closed-loop operation
EP2139556B1 (en) * 2007-03-26 2014-04-23 Remon Medical Technologies Ltd. Biased acoustic switch for implantable medical device
US8204599B2 (en) 2007-05-02 2012-06-19 Cardiac Pacemakers, Inc. System for anchoring an implantable sensor in a vessel
CA2685251A1 (en) * 2007-05-04 2008-11-13 Arizona Board Of Regents For And On Behalf Of Arizona State University Systems and methods for wireless transmission of biopotentials
US8825161B1 (en) 2007-05-17 2014-09-02 Cardiac Pacemakers, Inc. Acoustic transducer for an implantable medical device
US8718773B2 (en) 2007-05-23 2014-05-06 Ebr Systems, Inc. Optimizing energy transmission in a leadless tissue stimulation system
AU2008266678B2 (en) * 2007-06-14 2013-06-20 Cardiac Pacemakers, Inc. Multi-element acoustic recharging system
US8080064B2 (en) 2007-06-29 2011-12-20 Depuy Products, Inc. Tibial tray assembly having a wireless communication device
US8027724B2 (en) * 2007-08-03 2011-09-27 Cardiac Pacemakers, Inc. Hypertension diagnosis and therapy using pressure sensor
US8052745B2 (en) 2007-09-13 2011-11-08 Boston Scientific Scimed, Inc. Endoprosthesis
US9197470B2 (en) * 2007-10-05 2015-11-24 Innurvation, Inc. Data transmission via multi-path channels using orthogonal multi-frequency signals with differential phase shift keying modulation
US7953493B2 (en) 2007-12-27 2011-05-31 Ebr Systems, Inc. Optimizing size of implantable medical devices by isolating the power source
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
US8915866B2 (en) 2008-01-18 2014-12-23 Warsaw Orthopedic, Inc. Implantable sensor and associated methods
US8301262B2 (en) * 2008-02-06 2012-10-30 Cardiac Pacemakers, Inc. Direct inductive/acoustic converter for implantable medical device
US8725260B2 (en) 2008-02-11 2014-05-13 Cardiac Pacemakers, Inc Methods of monitoring hemodynamic status for rhythm discrimination within the heart
WO2009102640A1 (en) 2008-02-12 2009-08-20 Cardiac Pacemakers, Inc. Systems and methods for controlling wireless signal transfers between ultrasound-enabled medical devices
US8473069B2 (en) 2008-02-28 2013-06-25 Proteus Digital Health, Inc. Integrated circuit implementation and fault control system, device, and method
US8364276B2 (en) 2008-03-25 2013-01-29 Ebr Systems, Inc. Operation and estimation of output voltage of wireless stimulators
US8588926B2 (en) 2008-03-25 2013-11-19 Ebr Systems, Inc. Implantable wireless accoustic stimulators with high energy conversion efficiencies
EP2452721B1 (en) 2008-03-25 2013-11-13 EBR Systems, Inc. Method of manufacturing implantable wireless acoustic stimulators with high energy conversion efficiency
EP2265166B1 (en) 2008-03-25 2020-08-05 EBR Systems, Inc. Temporary electrode connection for wireless pacing systems
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
US8798761B2 (en) 2008-06-27 2014-08-05 Cardiac Pacemakers, Inc. Systems and methods of monitoring the acoustic coupling of medical devices
WO2010005571A2 (en) 2008-07-09 2010-01-14 Innurvation, Inc. Displaying image data from a scanner capsule
JP5362828B2 (en) 2008-07-15 2013-12-11 カーディアック ペースメイカーズ, インコーポレイテッド Implant assist for an acoustically enabled implantable medical device
US20100016911A1 (en) 2008-07-16 2010-01-21 Ebr Systems, Inc. Local Lead To Improve Energy Efficiency In Implantable Wireless Acoustic Stimulators
US7985252B2 (en) 2008-07-30 2011-07-26 Boston Scientific Scimed, Inc. Bioerodible endoprosthesis
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
EP2334230A1 (en) 2008-10-10 2011-06-22 Cardiac Pacemakers, Inc. Systems and methods for determining cardiac output using pulmonary artery pressure measurements
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
MX2011004817A (en) 2008-11-07 2011-07-28 Insuline Medical Ltd Device and method for drug delivery.
US8632470B2 (en) 2008-11-19 2014-01-21 Cardiac Pacemakers, Inc. Assessment of pulmonary vascular resistance via pulmonary artery pressure
US8126736B2 (en) 2009-01-23 2012-02-28 Warsaw Orthopedic, Inc. Methods and systems for diagnosing, treating, or tracking spinal disorders
US8685093B2 (en) 2009-01-23 2014-04-01 Warsaw Orthopedic, Inc. Methods and systems for diagnosing, treating, or tracking spinal disorders
US8694129B2 (en) 2009-02-13 2014-04-08 Cardiac Pacemakers, Inc. Deployable sensor platform on the lead system of an implantable device
US8267992B2 (en) 2009-03-02 2012-09-18 Boston Scientific Scimed, Inc. Self-buffering medical implants
US20100249882A1 (en) * 2009-03-31 2010-09-30 Medtronic, Inc. Acoustic Telemetry System for Communication with an Implantable Medical Device
EP2424588A4 (en) 2009-04-29 2013-05-22 Proteus Digital Health Inc Methods and apparatus for leads for implantable devices
US20100331918A1 (en) * 2009-06-30 2010-12-30 Boston Scientific Neuromodulation Corporation Moldable charger with curable material for charging an implantable pulse generator
US20100331915A1 (en) * 2009-06-30 2010-12-30 Hill Gerard J Acoustic activation of components of an implantable medical device
US8260432B2 (en) * 2009-06-30 2012-09-04 Boston Scientific Neuromodulation Corporation Moldable charger with shape-sensing means for an implantable pulse generator
US20100331919A1 (en) * 2009-06-30 2010-12-30 Boston Scientific Neuromodulation Corporation Moldable charger having hinged sections for charging an implantable pulse generator
US9468767B2 (en) * 2009-06-30 2016-10-18 Medtronic, Inc. Acoustic activation of components of an implantable medical device
US9399131B2 (en) * 2009-06-30 2016-07-26 Boston Scientific Neuromodulation Corporation Moldable charger with support members for charging an implantable pulse generator
US8786049B2 (en) 2009-07-23 2014-07-22 Proteus Digital Health, Inc. Solid-state thin-film capacitor
US20110082376A1 (en) * 2009-10-05 2011-04-07 Huelskamp Paul J Physiological blood pressure waveform compression in an acoustic channel
US9409013B2 (en) 2009-10-20 2016-08-09 Nyxoah SA Method for controlling energy delivery as a function of degree of coupling
US10751537B2 (en) 2009-10-20 2020-08-25 Nyxoah SA Arced implant unit for modulation of nerves
US10716940B2 (en) 2009-10-20 2020-07-21 Nyxoah SA Implant unit for modulation of small diameter nerves
US9192353B2 (en) * 2009-10-27 2015-11-24 Innurvation, Inc. Data transmission via wide band acoustic channels
US8376937B2 (en) * 2010-01-28 2013-02-19 Warsaw Orhtopedic, Inc. Tissue monitoring surgical retractor system
US8668732B2 (en) 2010-03-23 2014-03-11 Boston Scientific Scimed, Inc. Surface treated bioerodible metal endoprostheses
US8647259B2 (en) 2010-03-26 2014-02-11 Innurvation, Inc. Ultrasound scanning capsule endoscope (USCE)
US8594806B2 (en) 2010-04-30 2013-11-26 Cyberonics, Inc. Recharging and communication lead for an implantable device
US8718770B2 (en) 2010-10-21 2014-05-06 Medtronic, Inc. Capture threshold measurement for selection of pacing vector
US20150236236A1 (en) * 2011-02-24 2015-08-20 Cornell University Ultrasound wave generating apparatus
US8355784B2 (en) 2011-05-13 2013-01-15 Medtronic, Inc. Dynamic representation of multipolar leads in a programmer interface
EP2819745B1 (en) 2012-02-29 2018-10-10 The Cleveland Clinic Foundation System and method for generating composite patterns of stimulation or waveforms
US11871901B2 (en) 2012-05-20 2024-01-16 Cilag Gmbh International Method for situational awareness for surgical network or surgical network connected device capable of adjusting function based on a sensed situation or usage
US10052097B2 (en) 2012-07-26 2018-08-21 Nyxoah SA Implant unit delivery tool
US11253712B2 (en) 2012-07-26 2022-02-22 Nyxoah SA Sleep disordered breathing treatment apparatus
CA2879955C (en) 2012-07-26 2021-08-10 Adi Mashiach Implant sleep apnea treatment device including an antenna
US9907967B2 (en) 2012-07-26 2018-03-06 Adi Mashiach Transcutaneous power conveyance device
CN109939348B (en) 2013-06-17 2024-03-01 尼科索亚股份有限公司 Implant unit delivery tool
US9271064B2 (en) 2013-11-13 2016-02-23 Personics Holdings, Llc Method and system for contact sensing using coherence analysis
US9669224B2 (en) 2014-05-06 2017-06-06 Medtronic, Inc. Triggered pacing system
US9492671B2 (en) 2014-05-06 2016-11-15 Medtronic, Inc. Acoustically triggered therapy delivery
US10390720B2 (en) 2014-07-17 2019-08-27 Medtronic, Inc. Leadless pacing system including sensing extension
US9399140B2 (en) 2014-07-25 2016-07-26 Medtronic, Inc. Atrial contraction detection by a ventricular leadless pacing device for atrio-synchronous ventricular pacing
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
US9492669B2 (en) 2014-11-11 2016-11-15 Medtronic, Inc. Mode switching by a ventricular leadless pacing device
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
US9757574B2 (en) 2015-05-11 2017-09-12 Rainbow Medical Ltd. Dual chamber transvenous pacemaker
US10004906B2 (en) 2015-07-16 2018-06-26 Medtronic, Inc. Confirming sensed atrial events for pacing during resynchronization therapy in a cardiac medical device and medical device system
US10548977B1 (en) 2016-05-20 2020-02-04 Emery Korpas Pain relief utilizing a combination of polymer based materials
US10702704B2 (en) 2016-05-20 2020-07-07 E.K. Licensing, Llc Pain relief utilizing polymer based materials or a combination of LED bulbs, polymer based materials and a near field accelerator
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
CN117258169A (en) 2016-07-07 2023-12-22 加州大学评议会 Implant for stimulating tissue using ultrasound
DE102016120454A1 (en) * 2016-10-26 2018-04-26 Bundesrepublik Deutschland, Vertreten Durch Den Bundesminister Für Wirtschaft Und Energie, Dieser Vertreten Durch Den Präsidenten Der Bundesanstalt Für Materialforschung Und -Prüfung (Bam) Method and device for examining a sample
US10675476B2 (en) 2016-12-22 2020-06-09 Cardiac Pacemakers, Inc. Internal thoracic vein placement of a transmitter electrode for leadless stimulation of the heart
KR101905698B1 (en) 2017-02-17 2018-10-08 서강대학교 산학협력단 Implantable drug infusion pump for supporting full-duplex communication and system using the same
US20210128118A1 (en) * 2017-03-09 2021-05-06 Koninklijke Philips N.V. Sensor circuit and a signal analyzer for measuring an in-body property
EP3406185B1 (en) 2017-05-22 2021-02-24 Vestel Elektronik Sanayi ve Ticaret A.S. Implantable medical device and intra-bone wireless communication system and methods
US10694967B2 (en) 2017-10-18 2020-06-30 Medtronic, Inc. State-based atrial event detection
US20190125320A1 (en) 2017-10-30 2019-05-02 Ethicon Llc Control system arrangements for a modular surgical instrument
US11896322B2 (en) 2017-12-28 2024-02-13 Cilag Gmbh International Sensing the patient position and contact utilizing the mono-polar return pad electrode to provide situational awareness to the hub
US11013563B2 (en) 2017-12-28 2021-05-25 Ethicon Llc Drive arrangements for robot-assisted surgical platforms
US11109866B2 (en) 2017-12-28 2021-09-07 Cilag Gmbh International Method for circular stapler control algorithm adjustment based on situational awareness
US11832899B2 (en) 2017-12-28 2023-12-05 Cilag Gmbh International Surgical systems with autonomously adjustable control programs
US11864728B2 (en) 2017-12-28 2024-01-09 Cilag Gmbh International Characterization of tissue irregularities through the use of mono-chromatic light refractivity
US11672605B2 (en) 2017-12-28 2023-06-13 Cilag Gmbh International Sterile field interactive control displays
US11896443B2 (en) 2017-12-28 2024-02-13 Cilag Gmbh International Control of a surgical system through a surgical barrier
US11857152B2 (en) 2017-12-28 2024-01-02 Cilag Gmbh International Surgical hub spatial awareness to determine devices in operating theater
US11844579B2 (en) 2017-12-28 2023-12-19 Cilag Gmbh International Adjustments based on airborne particle properties
CN111712884A (en) * 2017-12-28 2020-09-25 爱惜康有限责任公司 Adjusting a device control program based on hierarchical background data in addition to data
US11534196B2 (en) 2018-03-08 2022-12-27 Cilag Gmbh International Using spectroscopy to determine device use state in combo instrument
US20210219909A1 (en) * 2018-05-14 2021-07-22 Alvin M Ostrow Wearable personal healthcare sensor apparatus
US11259807B2 (en) 2019-02-19 2022-03-01 Cilag Gmbh International Staple cartridges with cam surfaces configured to engage primary and secondary portions of a lockout of a surgical stapling device
US11654287B2 (en) 2019-08-30 2023-05-23 Ebr Systems, Inc. Pulse delivery device including slew rate detector, and associated systems and methods
CN111773550B (en) * 2020-07-10 2022-07-12 北京大学第三医院(北京大学第三临床医学院) Photochemical diagnosis and treatment equipment with multiple spectrum light sources

Family Cites Families (23)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US2786899A (en) 1951-08-02 1957-03-26 Sonotone Corp Piezoelectric transducers
US3536836A (en) * 1968-10-25 1970-10-27 Erich A Pfeiffer Acoustically actuated switch
US3672352A (en) 1969-04-09 1972-06-27 George D Summers Implantable bio-data monitoring method and apparatus
US3970987A (en) 1972-08-17 1976-07-20 Signal Science, Inc. Acoustical switch
GB1505130A (en) 1974-05-07 1978-03-22 Seiko Instr & Electronics Systems for detecting information in an artificial cardiac pacemaker
US4099530A (en) 1977-04-27 1978-07-11 American Pacemaker Corporation Cardiac pacer circuitry to facilitate testing of patient heart activity and pacer pulses
US4265241A (en) * 1979-02-28 1981-05-05 Andros Incorporated Implantable infusion device
US4481950A (en) * 1979-04-27 1984-11-13 Medtronic, Inc. Acoustic signalling apparatus for implantable devices
US4616640A (en) * 1983-11-14 1986-10-14 Steven Kaali Birth control method and device employing electric forces
GB8422876D0 (en) 1984-09-11 1984-10-17 Secr Defence Silicon implant devices
US4651740A (en) 1985-02-19 1987-03-24 Cordis Corporation Implant and control apparatus and method employing at least one tuning fork
DE3831809A1 (en) 1988-09-19 1990-03-22 Funke Hermann DEVICE DETERMINED AT LEAST PARTLY IN THE LIVING BODY
US5304206A (en) * 1991-11-18 1994-04-19 Cyberonics, Inc. Activation techniques for implantable medical device
US5800478A (en) 1996-03-07 1998-09-01 Light Sciences Limited Partnership Flexible microcircuits for internal light therapy
US5833603A (en) 1996-03-13 1998-11-10 Lipomatrix, Inc. Implantable biosensing transponder
US6140740A (en) * 1997-12-30 2000-10-31 Remon Medical Technologies, Ltd. Piezoelectric transducer
US6236889B1 (en) 1999-01-22 2001-05-22 Medtronic, Inc. Method and apparatus for accoustically coupling implantable medical device telemetry data to a telephonic connection
CA2365609A1 (en) * 1999-02-12 2000-08-17 Cygnus, Inc. Devices and methods for frequent measurement of an analyte present in a biological system
US6162238A (en) * 1999-02-24 2000-12-19 Aaron V. Kaplan Apparatus and methods for control of body lumens
US6170488B1 (en) * 1999-03-24 2001-01-09 The B. F. Goodrich Company Acoustic-based remotely interrogated diagnostic implant device and system
US6200265B1 (en) 1999-04-16 2001-03-13 Medtronic, Inc. Peripheral memory patch and access method for use with an implantable medical device
US6453201B1 (en) 1999-10-20 2002-09-17 Cardiac Pacemakers, Inc. Implantable medical device with voice responding and recording capacity
DE60107062T2 (en) 2000-03-31 2005-11-24 Advanced Bionics Corp., Sylmar COMPLETELY IMPLANTABLE COCHLEA MICROPROTHESIS WITH A VARIETY OF CONTACTS

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