US20110184508A2 - Improved tissue supporting devices - Google Patents

Improved tissue supporting devices Download PDF

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Publication number
US20110184508A2
US20110184508A2 US10/443,231 US44323103A US2011184508A2 US 20110184508 A2 US20110184508 A2 US 20110184508A2 US 44323103 A US44323103 A US 44323103A US 2011184508 A2 US2011184508 A2 US 2011184508A2
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US
United States
Prior art keywords
stent
temperature
shape memory
martensite
longitudinal dimension
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Abandoned
Application number
US10/443,231
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US20030208263A1 (en
Inventor
Paul Burmeister
Charles Euteneuer
Brian Brown
Paul Fordenbacher
Anthony Vrba
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Boston Scientific Scimed Inc
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Boston Scientific Scimed Inc
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Family has litigation
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Application filed by Boston Scientific Scimed Inc filed Critical Boston Scientific Scimed Inc
Priority to US10/443,231 priority Critical patent/US20110184508A2/en
Publication of US20030208263A1 publication Critical patent/US20030208263A1/en
Assigned to BOSTON SCIENTIFIC SCIMED, INC. reassignment BOSTON SCIENTIFIC SCIMED, INC. CHANGE OF NAME (SEE DOCUMENT FOR DETAILS). Assignors: SCIMED LIFE SYSTEMS, INC.
Publication of US20110184508A2 publication Critical patent/US20110184508A2/en
Abandoned legal-status Critical Current

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    • 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
    • A61F2/82Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/86Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure
    • A61F2/88Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure the wire-like elements formed as helical or spiral coils
    • 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
    • A61F2/82Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/844Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents folded prior to deployment
    • 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
    • A61F2/82Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/86Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure
    • A61F2/90Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure
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    • 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
    • A61F2/82Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/86Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure
    • A61F2/90Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure
    • A61F2/91Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes
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    • 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
    • A61F2/82Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/86Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure
    • A61F2/90Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure
    • A61F2/91Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes
    • A61F2/915Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes with bands having a meander structure, adjacent bands being connected to each other
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    • A61LMETHODS OR APPARATUS FOR STERILISING MATERIALS OR OBJECTS IN GENERAL; DISINFECTION, STERILISATION OR DEODORISATION OF AIR; CHEMICAL ASPECTS OF BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES; MATERIALS FOR BANDAGES, DRESSINGS, ABSORBENT PADS OR SURGICAL ARTICLES
    • A61L31/00Materials for other surgical articles, e.g. stents, stent-grafts, shunts, surgical drapes, guide wires, materials for adhesion prevention, occluding devices, surgical gloves, tissue fixation devices
    • A61L31/02Inorganic materials
    • A61L31/022Metals or alloys
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    • 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
    • A61F2/82Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/86Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure
    • A61F2/90Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure
    • A61F2/91Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes
    • A61F2/915Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes with bands having a meander structure, adjacent bands being connected to each other
    • A61F2002/91533Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes with bands having a meander structure, adjacent bands being connected to each other characterised by the phase between adjacent bands
    • 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
    • A61F2/82Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/86Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure
    • A61F2/90Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure
    • A61F2/91Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes
    • A61F2/915Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes with bands having a meander structure, adjacent bands being connected to each other
    • A61F2002/9155Adjacent bands being connected to each other
    • 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
    • A61F2/82Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/86Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure
    • A61F2/90Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure
    • A61F2/91Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes
    • A61F2/915Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes with bands having a meander structure, adjacent bands being connected to each other
    • A61F2002/9155Adjacent bands being connected to each other
    • A61F2002/91558Adjacent bands being connected to each other connected peak to peak
    • 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
    • A61F2/82Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/86Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure
    • A61F2/90Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure
    • A61F2/91Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes
    • A61F2/915Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure characterised by a net-like or mesh-like structure made from perforated sheet material or tubes, e.g. perforated by laser cuts or etched holes with bands having a meander structure, adjacent bands being connected to each other
    • A61F2002/9155Adjacent bands being connected to each other
    • A61F2002/91575Adjacent bands being connected to each other connected peak to trough
    • AHUMAN NECESSITIES
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    • 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
    • A61F2210/00Particular material properties of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2210/0014Particular material properties of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof using shape memory or superelastic materials, e.g. nitinol
    • A61F2210/0019Particular material properties of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof using shape memory or superelastic materials, e.g. nitinol operated at only one temperature whilst inside or touching the human body, e.g. constrained in a non-operative shape during surgery, another temperature only occurring before the operation
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    • A61F2210/0076Particular material properties of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof multilayered, e.g. laminated structures
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    • A61F2220/0025Connections or couplings between prosthetic parts, e.g. between modular parts; Connecting elements
    • A61F2220/0075Connections or couplings between prosthetic parts, e.g. between modular parts; Connecting elements sutured, ligatured or stitched, retained or tied with a rope, string, thread, wire or cable
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    • A61F2250/0029Special features of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof having different values of a given property or geometrical feature, e.g. mechanical property or material property, at different locations within the same prosthesis differing in bending or flexure capacity
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Definitions

  • This invention relates to tissue supporting devices in general and most particularly to vascular stents for placement in blood vessels.
  • a primary feature of the devices of this invention is that they are expandable within the body.
  • These devices are either expanded mechanically, such as by expansion of a balloon positioned inside the device, or are capable of releasing stored energy to self-expand themselves within the body.
  • the materials which have been used to make up these devices have included ordinary metals, shape memory alloys, various plastics, both biodegradable and not, and the like.
  • This invention is concerned with the use of these materials in a new multiple component arrangement which allows for initial self-expansion and subsequent deformation to a final enlarged diameter in the body.
  • Balloon expandable stents do not always expand uniformly around their circumference. As a result, healing may not take place in a consistent manner. If the stent is coated or covered, non-uniform expansion may tear the covering or coating. Additionally, long stents of this type may require long balloons which can be difficult to handle, difficult to size, and may not offer ideal performance in tortuous passages in blood vessels and the like.
  • the stents of the present invention provide the best features of both of these types of stents without their drawbacks.
  • the tissue supporting devices of this invention are generally cylindrical or tubular in overall shape and of such a configuration as to allow radial expansion for enlargement. They are often referred to herein in the general sense as “stents”. Furthermore, the devices are comprised of at least one component, element, constituent or portion which exhibits a tendency to self-expand the device to an expanded size and at least one other component, element, constituent or portion which is deformable so as to allow an external force, such as a balloon positioned within the body of the device, to further expand it to a final, larger desired expanded size.
  • the terms “component”, “telement”, “constituent” and “portion” are often referred to herein collectively as “portion”.
  • the devices of the invention are made of metal and most preferably of shape memory alloys.
  • a first portion is a resilient spring-like metal for self-expansion and a second portion is a deformable metal for final sizing.
  • a first portion is a self-expanding austenitic one and a second is a martensitic one capable of deformation.
  • the “portions” may be discrete or merely different phases of an alloy.
  • the most preferred embodiment of the invention is a stent, preferably of shape memory alloy.
  • the most preferred shape memory alloy is Ni—Ti, although any of the other known shape memory alloys may be used as well.
  • Such other alloys include: Au—Cd, Cu—Zn, In—Ti, Cu—Zn—Al, Ti—Nb, Au—Cu—Zn, Cu—Zn—Sn, Cu—Zn—Si, Cu—Al—Ni, Ag—Cd, Cu—Sn, Cu—Zn—Ga, Ni—Al, Fe—Pt, U—Nb, Ti—Pd—Ni, Fe—Mn—Si, and the like. These alloys may also be doped with small amounts of other elements for various property modifications as may be desired and as is known in the art.
  • FIG. 1 is a braided stent according to one embodiment of this invention.
  • FIG. 2 is a graph showing the martensitic/austenitic temperature transformation curve and the superelastic area of a shape memory alloy.
  • FIG. 3 is an end view of a layered stent having two discrete components according to one aspect of this invention.
  • FIGS. 4 a and 4 b are graphs showing the martensitic/austenitic temperature transformation curves of the layers in the stent of FIG. 3 .
  • FIGS. 5 a and 5 b are views of another embodiment of the invention comprised of alternating rings of shape memory alloy.
  • FIG. 6 is a showing of a stent fragment of a braided version of a shape memory stent of this invention.
  • FIG. 7 is a graph showing a temperature window for a shape memory alloy to be used in yet another stent version of this invention.
  • FIG. 7 a is a graph showing expansion of a stent with temperature.
  • FIG. 7 b is a graph of the same type, the stent having been cold-worked.
  • FIG. 7 c is a graph of the same type, the stent having had pseudoelastic prestraining.
  • FIG. 7 d is a graph of the same type, the stent having amnesia inducement.
  • FIGS. 8-11 show various expandable configurations (closed and open) illustrated in fragment which may be used in the stents of this invention.
  • FIGS. 9 a and 9 b show a preferred embodiment of an articulated stent.
  • FIG. 12 shows another version of an expandable stent of the invention.
  • FIG. 13 shows yet another version of a stent which may be used with the invention.
  • FIG. 14 is a schematic showing of a braided stent made up of a plurality of strands.
  • FIG. 15 is a detail of a single strand from the stent of FIG. 14 showing that the strand is made up of a plurality of wires of two different types.
  • FIG. 16 is a cross-sectional view taken along line 16 - 16 of FIG. 15 showing the two different types of wire.
  • a stent 10 is shown comprised of braided or interwoven metal strands 12 and 14 .
  • Strands 12 are of a resilient spring-like metal such as spring steel, Elgiloy for example.
  • strands 12 are spirally extending in the same direction, spiraling to the right as seen in FIG. 1 .
  • Strands 14 are of a deformable or annealed metal such as stainless steel and are preferably spiraled in the opposite direction as strands 12 , as shown in FIG. 1 .
  • stent 10 may be readily loaded on a catheter as by placing it over an uninflated balloon on a balloon catheter and compressing it tightly around the balloon and then placing a sheath over the stent to hold it in place during the transluminal placement procedure. Once in place, the sheath is removed, for example slid back, to expose the stent, allowing it to self-expand by force of the resilient strands 12 to substantially assume a self-expanded shape/size. Some self-expansion may be restrained if held back by strands 14 .
  • the balloon may be expanded by inflation from within the stent to exert an outward radial force on the stent and further enlarge it by stretching and deforming the deformable metal of strands 14 .
  • This may be aided by building into strands 14 , a series of readily deformable structures or means such as bends or kinks 16 as shown in FIG. 1 . It can be seen that a permanent adjustable size beyond the self-expanded size may be obtained with this embodiment.
  • many configurations other than braided may be readily devised to take advantage of this two component concept, including various of the subsequent configurations-described hereinbelow.
  • the stent may be initially deployed without a balloon; the balloon following on a separate catheter.
  • shape memory alloys make use of shape memory alloys and some of their unique properties, primarily their special types of deformation i.e., shape memory deformation in martensite and/or superelastic deformation in austenite.
  • the term “superelasticity” is used to describe the property of certain shape memory alloys to return to their original shape upon unloading after a substantially deformation while in their austenitic state.
  • Superelastic alloys can be strained while in their austenitic state more than ordinary spring materials without being plastically deformed. This unusually large elasticity in the austenitic state is also called “pseudoelasticity”, because the mechanism is nonconventional in nature, or is also sometimes referred to as “transformational superelasticity” because it is caused by a stress induced phase transformation. Alloys that show superelasticity also undergo a thermoelastic martensitic transformation which is also the prerequisite for the shape memory effect. Superelasticity and shape memory effects are therefore closely related. Superelasticity can even be considered part of the shape memory effect.
  • Ni—Ti alloys The shape memory and superelasticity effects are particularly pronounced in Ni—Ti alloys. This application will therefore focus on these alloys as the preferred shape memory alloys.
  • the shape memory effect in Ni—Ti alloys has been described many times and is well known.
  • martensite forms on cooling from the body centered cubic high temperature phase, termed austenite, by a shear type of process. This martensitic phase is heavily twinned. In the absence of any externally applied force transformation takes place with almost no external macroscopic shape change. The martensite can be easily deformed by a “flipping over” type of shear until a single orientation is achieved. This process is also called “detwinning”.
  • a plot of the volume fraction of austenite as a function of temperature provides a curve of the type shown schematically in FIG. 2 .
  • the complete transformation cycle is characterized by the following temperatures: austenite start temperature (A s ), austenite finish temperature (A f ), both of which are involved in the first part (1) of an increasing temperature cycle and martensite start temperature (M s ) and martensite finish temperature (M f ), both of which are involved in the second part (2) of a decreasing temperature cycle.
  • FIG. 2 represents the transformation cycle without applied stress.
  • martensite can be stress-induced. Stress induced martensite is deformed by detwinning as described above. Less energy is needed to stress induce and deform martensite than to deform the austenite by conventional mechanisms. Up to about 8% strain can be accommodated by this process (single crystals of specific alloys can show as much as about 25% pseudoelastic strain in certain directions).
  • austenite is the thermodynamically stable phase at temperatures between A s and M d under no-load conditions, the material springs back into its original shape when the stress is no longer applied.
  • the martensitic state of this alloy may be used to advantage in the two component concept of this invention.
  • a layered construction may be provided in a stent 30 (shown in end view) which is generally a hollow cylindrical or tubular body in shape but which may be formed in a wide variety of specific configurations or patterns to foster radial expansion of the body as exemplified in FIGS. 1, 5 , 6 and in subsequent FIGS. 8-11 .
  • the inner layer is 32 and the outer layer is 34 .
  • this may be reversed and also a plurality of layers, alternating or otherwise, may be utilized in this particular embodiment.
  • Stent 30 is made to a fabricated size and shape (parent shape) which provides austenitic layer 32 its parent shape and size i.e., its superelastic high temperature shape and size.
  • the Ni—Ti alloy of austenitic layer 32 is selected so as to have a transition temperature range between its austenitic and martensitic states which is lower than body temperature as to ensure that in the body and at body temperatures the austenitic state will always prevail.
  • martensitic layer 34 is of a Ni—Ti alloy having a transition temperature range significantly greater than body temperature so as to ensure that under body conditions the martensitic state will always prevail and the alloy will never transform to austenite in stent use.
  • FIGS. 4 a and 4 b demonstrate the relative transition temperatures of layers 32 and 34 , respectively for purposes of this invention. It can be seen from these graphs that the normal condition of layer 32 ( FIG. 4 a ) at body temperatures and higher is the austenitic state while the normal condition of layer 34 ( FIG. 4 b ) at body temperatures is martensitic.
  • the austenitic portion may be made with any standard metallurgical technique and vapor deposit the martensitic portion on its surface.
  • Other manufacturing techniques such as diffusion bonding, welding, ion beam deposition, and various others will be apparent to those familiar with this art.
  • Such a stent may be compressed or constrained (deformed to a small diameter) onto a balloon catheter as described for the previous embodiment and captured within a sheath.
  • austenitic layer 32 may stress induce to a martensitic state.
  • the stent may be cooled below the transition temperature of layer 32 to facilitate its deformation and constrainment. Martensitic layer 34 merely undergoes deformation.
  • the stent may be “loaded” onto a balloon catheter.
  • layer 32 will remain martensite until the constraint is removed.
  • stent 30 When released in place in the body, stent 30 will expand to a percentage of its self-expanded size and shape due to the transformation of layer 32 from martensite to austenite at which point the balloon may be used to radially expand the stent to a greater permanent diameter by deforming martensitic layer 34 .
  • initial deployment can take place without a balloon which may be separately inserted after deployment.
  • the two component concept of the invention in the layered embodiment of FIG. 3 requires both the martensitic and austenitic phase characteristics of shape memory alloy(s) in the two discrete components 32 and 34 .
  • the stent is fabricated in such a way that the austenitic layer 32 tends to self-expand stent 30 to a predetermined fabricated diameter (parent shape, also referred to herein as “shape memorized diameter”).
  • the martensitic layer 34 tends to hold back this self-expansion, preventing full expansion.
  • the stent may only be able to self-expand to 75% of its full possible diameter (as determined by the austenitic layer). Therefore, expansion beyond 75% is accomplished by an applied external force, as by the balloon inside the stent.
  • the stent not be expanded beyond its normal fabricated diameter for the austenitic layer 32 will have the tendency of making the stent diameter smaller as it tries to recover its fabricated diameter (parent shape). If the stent is subjected to a temperature above body temperature and above the transition temperature of the martensitic layer (which is clinically unlikely), the stent will self-expand to the fabricated diameter only. Depending on design size there are thus provided permanent stents capable of fulfilling any needed range of sizes with an adjustable sizing capability.
  • the desired properties of the shape memory alloys required for use in this invention may be obtained by alloy composition and working and heat treatment of the alloys, in various combinations or singly.
  • the material is capable of taking high strains and recovering after the load is released.
  • FIGS. 5 and 6 other stent constructions are shown which are similar to the layered version of FIG. 3 in so far as utilization of the two component concept of this invention is concerned.
  • FIGS. 5 a and 5 b shows a stent 50 made up of alternating expandable rings 52 and 54 of austenitic and martensitic alloys, respectively, analogous to layers 32 and 34 of the FIG. 3 embodiment.
  • Rings 52 and 54 for example are interconnected by strut members 56 which may be of any material capable of rigidly holding the rings together. Other interconnector means may be used.
  • strut members 56 may be of any material capable of rigidly holding the rings together.
  • Other interconnector means may be used.
  • the placement of strut members 56 does not require them to take part in the radial expansion of the stent and they can therefore be of a relatively ordinary material such as stainless steel.
  • strands 62 extending to the right in FIG. 6 are an alloy in the austenitic state whereas strands 64 extending to the left in FIG. 6 are an alloy in the martensitic state.
  • an alloy composition can be selected such that it has a phase transition temperature window that bounds the proposed operating temperatures of the stent, such as the normal body temperature range. Within this transitional window or zone, the material undergoes the phase transition and is effectively compositionally comprised of a ratio of austenitic to martensitic phase depending on the temperature of the stent.
  • This ratio should be selected so as to provide sufficient radial force from the austenite phase while still allowing for further expansion of the martensite phase with a mechanical expansion means such as a balloon.
  • a Ni—Ti alloy of about 50/50 atomic wt. % composition (range about 49/51%) will provide an acceptable “window” for this embodiment, the two components are the austenite and martensite phases of the nitinol.
  • the method of making a stent may be described as follows. Age the shape memory material (Ni Ti) until body temperature falls somewhere within the transformation window. Therefore the stent will not fully recover to its high temperature shape at body temperature. An example of this technique is described below.
  • a stent of tubular 50.8% Ni balance Ti was prepared having a 1.5 mm diameter. It was substantially all austenite at room temperature, the A f being about 15-20° C. and therefore being superelastic at room temperature.
  • the stent was cooled to below room temperature to form substantially all martensite and mechanically expanded to 4.7 mm in diameter. It was maintained at the 4.7 mm in diameter and heat treated at 500° C. for 30 minutes and water quenched. Finally, it was again cooled to below room temperature to form substantially all martensite and compressed to a diameter of 1.5 mm. After deployment and at body temperature the stent has a diameter of 3.5 mm. At about 70% of full expansion, i.e., about 40° C. it had a diameter of 4.5 mm and at 42° C. it had a fully expanded diameter of 4.7 mm.
  • FIG. 7 a shows a temperature versus diameter plot.
  • Three methods of modifying the slope of the line on the temperature versus diameter graph are cold work, pseudoelastic prestraining, and amnesia inducement, illustrated in FIGS. 7 b , 7 c and 7 d , respectively.
  • FIG. 7 b is an example of a temperature versus diameter plot for a cold worked part.
  • FIG. 7 a above shows an example of a part without cold work.
  • the A f temperature for the second plateau would be above body temperature such that there is no additional self expansion in this region (70 to 100% expansion) a mechanical device, like a balloon, can then be used to custom size the stent between 70% and 100% of the high temperature shape. Results of such a technique is shown in FIG. 7 c.
  • nitinol is cycle amnesia. This was also discussed about in the article referred to immediately above. As nitinol is cycled from its heat set shape as shown in FIG. 7 d , there is an increase in the amount of amnesia to recover to the heat set shape with each cycle. As long as this amnesia is not caused by permanent plastic deformation, the amnesia can be removed by heating the part above M d . This shows there is martensite left in the part after cycling which is preventing full recovery in the austenite phase (just above A f ). This presence of non recoverable martensite (below M d ) is what may be used for the balloon expansion region of the stent.
  • the version shown in FIGS. 10 a and 10 b may be modified as shown in FIGS. 10 c and 10 d (closed and open, respectively) by omitting portions (indicated at 100 in FIGS. 10 c and 10 d ) as to render the stent flexible for articulation. This may be done to other of the structures as well to improve flexibility.
  • FIG. 12 Yet another version of a device incorporating the two component concept of the invention is shown in FIG. 12 .
  • the stent includes a self-expanding component 112 and a deformable, external force expandable component 114 .
  • Self expanding component 112 may be resilient spring-like metal such a stainless steel or it may preferably be a shape memory alloy in the austenitic state.
  • Component 114 may be any deformable metal or the like such as annealed stainless steel or preferably a shape memory alloy in the martensitic state.
  • the two components may simply be mechanically, welded or bonded together. Functions and operations are as described hereinabove.
  • FIG. 13 a version analogous to the embodiment of FIG. 12 is shown in which the two component concept is again embodied as different zones or portions of a single metal material.
  • a stent 120 (fragment showing) is of a self-expanding component 122 and a deformable component 124 , both of which may be a single metal as spring steel or austenitic Ni—Ti which has been appropriately treated with respect to component 124 as by localized heat treatment or the like to alter the characteristics of the material of the 122 component so as to render it deformable or martensitic, depending on whether it is merely resilient or is austenitic.
  • function and operation are the same as with other embodiments.
  • each strand 150 in the stent is a micro-cable. That is, each strand is made up of a plurality of wires 152 and 154 as is seen in FIGS. 15 and 16 .
  • Each of the wires 152 and 154 consists of two different nitinol alloys as seen best in FIG. 16 , or one nitinol and one ordinary metal such as stainless steel, platinum or tantalum. The latter two would provide enhanced radiopacity.
  • One nitinol alloy wire 154 has an austenitic finish (A f ) temperature less than body temperature.
  • the other wire 152 could be nitinol having an A s (austenitic start) greater than body temperature. Also, it could be an ordinary metal. Additionally, one or more of the strands may be of a biodegradable material such as a plastic or may be of a material including an absorbable drug.
  • Radiopaque portions or coatings may be included on any parts of these stents as is known in the prior art.

Abstract

A new multiple component stent arrangement which allows for initial self-expansion and subsequent deformation to a final enlarged size.

Description

    CROSS-REFERENCE TO RELATED APPLICATIONS
  • This application is a Continuation application from Ser. No. 09/427,291, filed on Oct. 26, 1999, which is a Continuation application from Ser. No. 08/737,492 filed on May 18, 1995, as a §371 of PCT/US95/06228 filed May 18, 1995, the contents of which is hereby incorporated by reference, now U.S. Pat. No. 6,582,461, which is a continuation-in-part of application Ser. No. 08/246,320, filed May 19, 1994. This application is also a continuation of application Ser. No. 09/172,590 filed on Oct. 14, 1998, now 6,451,052, which is a Division of application Ser. No. 08/737,492 filed on May 18, 1995, as a §371 of PCT/US95/06228 filed May 18, 1995, now U.S. Pat. No. 6,582,461, which is a continuation-in-part of application Ser. No. 08/246,320, filed May 19, 1994.
  • BACKGROUND OF THE INVENTION
  • This invention relates to tissue supporting devices in general and most particularly to vascular stents for placement in blood vessels. A primary feature of the devices of this invention is that they are expandable within the body.
  • In the past, such devices have been provided for implantation within body passageways. These devices have been characterized by the ability to be enlarged radially, often having been introduced into the desired position in the body as by percutaneous techniques or surgical techniques.
  • These devices are either expanded mechanically, such as by expansion of a balloon positioned inside the device, or are capable of releasing stored energy to self-expand themselves within the body.
  • The materials which have been used to make up these devices have included ordinary metals, shape memory alloys, various plastics, both biodegradable and not, and the like.
  • This invention is concerned with the use of these materials in a new multiple component arrangement which allows for initial self-expansion and subsequent deformation to a final enlarged diameter in the body.
  • Balloon expandable stents do not always expand uniformly around their circumference. As a result, healing may not take place in a consistent manner. If the stent is coated or covered, non-uniform expansion may tear the covering or coating. Additionally, long stents of this type may require long balloons which can be difficult to handle, difficult to size, and may not offer ideal performance in tortuous passages in blood vessels and the like.
  • Thus, when addressing such issues, self-expandable stents have been thought to be generally more desirable. Unfortunately, one cannot control the degree of expansion and hence the degree of embedment in the vessel wall. It has been determined that a stent must be embedded to some degree to be clinically satisfactory.
  • The stents of the present invention provide the best features of both of these types of stents without their drawbacks.
  • SUMMARY OF THE INVENTION
  • The tissue supporting devices of this invention are generally cylindrical or tubular in overall shape and of such a configuration as to allow radial expansion for enlargement. They are often referred to herein in the general sense as “stents”. Furthermore, the devices are comprised of at least one component, element, constituent or portion which exhibits a tendency to self-expand the device to an expanded size and at least one other component, element, constituent or portion which is deformable so as to allow an external force, such as a balloon positioned within the body of the device, to further expand it to a final, larger desired expanded size. The terms “component”, “telement”, “constituent” and “portion” are often referred to herein collectively as “portion”.
  • Preferably, the devices of the invention are made of metal and most preferably of shape memory alloys.
  • In one embodiment, a first portion is a resilient spring-like metal for self-expansion and a second portion is a deformable metal for final sizing. In a more preferred shape memory embodiment, a first portion is a self-expanding austenitic one and a second is a martensitic one capable of deformation. In the case of shape memory embodiments the “portions” may be discrete or merely different phases of an alloy.
  • The most preferred embodiment of the invention is a stent, preferably of shape memory alloy. The most preferred shape memory alloy is Ni—Ti, although any of the other known shape memory alloys may be used as well. Such other alloys include: Au—Cd, Cu—Zn, In—Ti, Cu—Zn—Al, Ti—Nb, Au—Cu—Zn, Cu—Zn—Sn, Cu—Zn—Si, Cu—Al—Ni, Ag—Cd, Cu—Sn, Cu—Zn—Ga, Ni—Al, Fe—Pt, U—Nb, Ti—Pd—Ni, Fe—Mn—Si, and the like. These alloys may also be doped with small amounts of other elements for various property modifications as may be desired and as is known in the art.
  • The invention will be specifically described hereinbelow with reference to stents, a preferred embodiment of the invention although it is broadly applicable to tissue support devices in general.
  • BRIEF DESCRIPTION OF THE FIGURES
  • FIG. 1 is a braided stent according to one embodiment of this invention.
  • FIG. 2 is a graph showing the martensitic/austenitic temperature transformation curve and the superelastic area of a shape memory alloy.
  • FIG. 3 is an end view of a layered stent having two discrete components according to one aspect of this invention.
  • FIGS. 4 a and 4 b are graphs showing the martensitic/austenitic temperature transformation curves of the layers in the stent of FIG. 3.
  • FIGS. 5 a and 5 b are views of another embodiment of the invention comprised of alternating rings of shape memory alloy.
  • FIG. 6 is a showing of a stent fragment of a braided version of a shape memory stent of this invention.
  • FIG. 7 is a graph showing a temperature window for a shape memory alloy to be used in yet another stent version of this invention.
  • FIG. 7 a is a graph showing expansion of a stent with temperature.
  • FIG. 7 b is a graph of the same type, the stent having been cold-worked.
  • FIG. 7 c is a graph of the same type, the stent having had pseudoelastic prestraining.
  • FIG. 7 d is a graph of the same type, the stent having amnesia inducement.
  • FIGS. 8-11 show various expandable configurations (closed and open) illustrated in fragment which may be used in the stents of this invention. FIGS. 9 a and 9 b show a preferred embodiment of an articulated stent.
  • FIG. 12 shows another version of an expandable stent of the invention.
  • FIG. 13 shows yet another version of a stent which may be used with the invention.
  • FIG. 14 is a schematic showing of a braided stent made up of a plurality of strands.
  • FIG. 15 is a detail of a single strand from the stent of FIG. 14 showing that the strand is made up of a plurality of wires of two different types.
  • FIG. 16 is a cross-sectional view taken along line 16-16 of FIG. 15 showing the two different types of wire.
  • DETAILED DESCRIPTION OF THE INVENTION
  • Preferred embodiments of this invention are described below with particular reference to the accompanying drawing Figures.
  • Referring first to the embodiment shown in FIG. 1, a stent 10 is shown comprised of braided or interwoven metal strands 12 and 14. Strands 12 are of a resilient spring-like metal such as spring steel, Elgiloy for example. Preferably, strands 12 are spirally extending in the same direction, spiraling to the right as seen in FIG. 1. Strands 14 are of a deformable or annealed metal such as stainless steel and are preferably spiraled in the opposite direction as strands 12, as shown in FIG. 1.
  • Given such a stent construction of two components i.e., strands 12 and. 14, it can be seen that stent 10 may be readily loaded on a catheter as by placing it over an uninflated balloon on a balloon catheter and compressing it tightly around the balloon and then placing a sheath over the stent to hold it in place during the transluminal placement procedure. Once in place, the sheath is removed, for example slid back, to expose the stent, allowing it to self-expand by force of the resilient strands 12 to substantially assume a self-expanded shape/size. Some self-expansion may be restrained if held back by strands 14. To finally adjust the size of the stent, the balloon may be expanded by inflation from within the stent to exert an outward radial force on the stent and further enlarge it by stretching and deforming the deformable metal of strands 14. This may be aided by building into strands 14, a series of readily deformable structures or means such as bends or kinks 16 as shown in FIG. 1. It can be seen that a permanent adjustable size beyond the self-expanded size may be obtained with this embodiment. It is to be noted that many configurations other than braided may be readily devised to take advantage of this two component concept, including various of the subsequent configurations-described hereinbelow. Also, it should be noted that, although not preferred, the stent may be initially deployed without a balloon; the balloon following on a separate catheter.
  • Referring now to subsequent features, other preferred embodiments of the invention will be described which make use of shape memory alloys and some of their unique properties, primarily their special types of deformation i.e., shape memory deformation in martensite and/or superelastic deformation in austenite.
  • The term “superelasticity” is used to describe the property of certain shape memory alloys to return to their original shape upon unloading after a substantially deformation while in their austenitic state. Superelastic alloys can be strained while in their austenitic state more than ordinary spring materials without being plastically deformed. This unusually large elasticity in the austenitic state is also called “pseudoelasticity”, because the mechanism is nonconventional in nature, or is also sometimes referred to as “transformational superelasticity” because it is caused by a stress induced phase transformation. Alloys that show superelasticity also undergo a thermoelastic martensitic transformation which is also the prerequisite for the shape memory effect. Superelasticity and shape memory effects are therefore closely related. Superelasticity can even be considered part of the shape memory effect.
  • The shape memory and superelasticity effects are particularly pronounced in Ni—Ti alloys. This application will therefore focus on these alloys as the preferred shape memory alloys. The shape memory effect in Ni—Ti alloys has been described many times and is well known.
  • In near-equiatomic Ni—Ti alloys, martensite forms on cooling from the body centered cubic high temperature phase, termed austenite, by a shear type of process. This martensitic phase is heavily twinned. In the absence of any externally applied force transformation takes place with almost no external macroscopic shape change. The martensite can be easily deformed by a “flipping over” type of shear until a single orientation is achieved. This process is also called “detwinning”.
  • If a deformed martensite is now heated, it reverts to austenite. The crystallographic restrictions are such that it transforms back to the initial orientation thereby restoring the original shape. Thus, if a straight piece of wire in the austenitic condition is cooled to form martensite it remains straight. If it is now deformed by bending, the twinned martensite is converted to deformed martensite. On heating, the transformation back to austenite occurs and the bent wire becomes straight again. This process illustrates the shape memory deformation referred to above.
  • The transformation from austenite to martensite and the reverse transformation from martensite to austenite do not take place at the same temperature. A plot of the volume fraction of austenite as a function of temperature provides a curve of the type shown schematically in FIG. 2. The complete transformation cycle is characterized by the following temperatures: austenite start temperature (As), austenite finish temperature (Af), both of which are involved in the first part (1) of an increasing temperature cycle and martensite start temperature (Ms) and martensite finish temperature (Mf), both of which are involved in the second part (2) of a decreasing temperature cycle.
  • FIG. 2 represents the transformation cycle without applied stress. However, if a stress is applied in the temperature range between As and Md, martensite can be stress-induced. Stress induced martensite is deformed by detwinning as described above. Less energy is needed to stress induce and deform martensite than to deform the austenite by conventional mechanisms. Up to about 8% strain can be accommodated by this process (single crystals of specific alloys can show as much as about 25% pseudoelastic strain in certain directions). As austenite is the thermodynamically stable phase at temperatures between As and Md under no-load conditions, the material springs back into its original shape when the stress is no longer applied.
  • It becomes increasingly difficult to stress-induce martensite at increasing temperatures above Af. Eventually, it is easier to deform the material by conventional mechanisms (movement of the dislocation, slip) than by inducing and deforming martensite. The temperature at which martensite can no longer be stress-induced is called Md. Above Md, Ni—Ti alloys are deformed like ordinary materials by slipping.
  • Additional information regarding shape memory alloys is found in the following references, all of which are incorporated fully herein by reference:
    • Super Elastic Nickel-Titanium Wires” by Dieter Stockel and Weikang Yu of Raychem Corporation, Menlo Park, Calif., copy received November 1992;
    • Metals Handbook, Tenth Edition, Vol. 2, Properties and Selection: Nonferrous Alloys and Special-Purpose Materials, “Shape Memory Alloys” by Hodgson, Wu and Biermann, pp. 897-902; and,
    • In Press, Titanium Handbook, ASM (1994), Section entitled “Structure and Properties of Ti—Ni Alloys by T. W. Duerig and A. R. Pelton.
  • Since the most preferred shape memory alloy is Ni—Ti, the martensitic state of this alloy may be used to advantage in the two component concept of this invention.
  • For example, with reference to FIG. 3, a layered construction may be provided in a stent 30 (shown in end view) which is generally a hollow cylindrical or tubular body in shape but which may be formed in a wide variety of specific configurations or patterns to foster radial expansion of the body as exemplified in FIGS. 1, 5, 6 and in subsequent FIGS. 8-11.
  • Stent 30 is comprised of at least two layers 32 and 34, one of which 32 is a Ni—Ti alloy (50.8 atomic wt. % Ni, balance Ti, transition temperature of Af=0° C.) and normally in the austenitic state, the other of which 34 is a Ni—Ti (49.4 atomic wt. % Ni, balance Ti, transition temperature Af=60° C.) and normally in the martensitic state. Preferably, the inner layer is 32 and the outer layer is 34. However, this may be reversed and also a plurality of layers, alternating or otherwise, may be utilized in this particular embodiment.
  • Stent 30 is made to a fabricated size and shape (parent shape) which provides austenitic layer 32 its parent shape and size i.e., its superelastic high temperature shape and size. Obviously, in its as fabricated condition, the Ni—Ti alloy of austenitic layer 32 is selected so as to have a transition temperature range between its austenitic and martensitic states which is lower than body temperature as to ensure that in the body and at body temperatures the austenitic state will always prevail.
  • On the other hand, martensitic layer 34 is of a Ni—Ti alloy having a transition temperature range significantly greater than body temperature so as to ensure that under body conditions the martensitic state will always prevail and the alloy will never transform to austenite in stent use. This is shown in the graphs of FIGS. 4 a and 4 b which demonstrate the relative transition temperatures of layers 32 and 34, respectively for purposes of this invention. It can be seen from these graphs that the normal condition of layer 32 (FIG. 4 a) at body temperatures and higher is the austenitic state while the normal condition of layer 34 (FIG. 4 b) at body temperatures is martensitic.
  • To manufacture the layered construction, one may make the austenitic portion with any standard metallurgical technique and vapor deposit the martensitic portion on its surface. Other manufacturing techniques such as diffusion bonding, welding, ion beam deposition, and various others will be apparent to those familiar with this art.
  • Such a stent may be compressed or constrained (deformed to a small diameter) onto a balloon catheter as described for the previous embodiment and captured within a sheath. During the constrainment, austenitic layer 32 may stress induce to a martensitic state. In the alternative, the stent may be cooled below the transition temperature of layer 32 to facilitate its deformation and constrainment. Martensitic layer 34 merely undergoes deformation. Thus the stent may be “loaded” onto a balloon catheter. However, with temperature changes occurring up to body temperature, layer 32 will remain martensite until the constraint is removed. When released in place in the body, stent 30 will expand to a percentage of its self-expanded size and shape due to the transformation of layer 32 from martensite to austenite at which point the balloon may be used to radially expand the stent to a greater permanent diameter by deforming martensitic layer 34. On the other hand, initial deployment can take place without a balloon which may be separately inserted after deployment.
  • The two component concept of the invention in the layered embodiment of FIG. 3 requires both the martensitic and austenitic phase characteristics of shape memory alloy(s) in the two discrete components 32 and 34.
  • Preferably, the stent is fabricated in such a way that the austenitic layer 32 tends to self-expand stent 30 to a predetermined fabricated diameter (parent shape, also referred to herein as “shape memorized diameter”). The martensitic layer 34 tends to hold back this self-expansion, preventing full expansion. For example, the stent may only be able to self-expand to 75% of its full possible diameter (as determined by the austenitic layer). Therefore, expansion beyond 75% is accomplished by an applied external force, as by the balloon inside the stent. It is suggested that the stent not be expanded beyond its normal fabricated diameter for the austenitic layer 32 will have the tendency of making the stent diameter smaller as it tries to recover its fabricated diameter (parent shape). If the stent is subjected to a temperature above body temperature and above the transition temperature of the martensitic layer (which is clinically unlikely), the stent will self-expand to the fabricated diameter only. Depending on design size there are thus provided permanent stents capable of fulfilling any needed range of sizes with an adjustable sizing capability.
  • As is known in the art, the desired properties of the shape memory alloys required for use in this invention may be obtained by alloy composition and working and heat treatment of the alloys, in various combinations or singly.
  • Manufacturing techniques influence the phase characteristics of the material. Alloy composition, work history, and heat treatment all influence the final characteristics. At a specific operating temperature, say body temperature, the austenite phase material will have a transition temperature below body temperature (i.e., Af=0° C.). The material is capable of taking high strains and recovering after the load is released. The martensite phase material will have a higher transition temperature than body temperature (i.e., Af=60° C.), and is characteristically soft and pliable and retains the deformed shape after load removal. This martensite deformation is caused by detwinning, not the typical plastic deformation, or yielding, of crystal slip.
  • With reference to FIGS. 5 and 6, other stent constructions are shown which are similar to the layered version of FIG. 3 in so far as utilization of the two component concept of this invention is concerned.
  • FIGS. 5 a and 5 b shows a stent 50 made up of alternating expandable rings 52 and 54 of austenitic and martensitic alloys, respectively, analogous to layers 32 and 34 of the FIG. 3 embodiment. Rings 52 and 54 for example are interconnected by strut members 56 which may be of any material capable of rigidly holding the rings together. Other interconnector means may be used. As can be seen in FIG. 5 b, the placement of strut members 56 does not require them to take part in the radial expansion of the stent and they can therefore be of a relatively ordinary material such as stainless steel.
  • Referring now to FIG. 6, a braided or interwoven construction is shown similar in construction to that of the embodiment of FIG. 1. In this embodiment, strands 62 extending to the right in FIG. 6 are an alloy in the austenitic state whereas strands 64 extending to the left in FIG. 6 are an alloy in the martensitic state.
  • Referring now to the graph of FIG. 7, it is demonstrated that the two component concept of the invention may be embodied in two phases, i.e., components of a single shape memory alloy and need not be in the form of two discrete components such as layers, members, wires, etc. In the graph of FIG. 7, it can be seen that an alloy composition can be selected such that it has a phase transition temperature window that bounds the proposed operating temperatures of the stent, such as the normal body temperature range. Within this transitional window or zone, the material undergoes the phase transition and is effectively compositionally comprised of a ratio of austenitic to martensitic phase depending on the temperature of the stent. This ratio should be selected so as to provide sufficient radial force from the austenite phase while still allowing for further expansion of the martensite phase with a mechanical expansion means such as a balloon. Selecting body temperature as the operating temperature, a Ni—Ti alloy of about 50/50 atomic wt. % composition (range about 49/51%) will provide an acceptable “window” for this embodiment, the two components are the austenite and martensite phases of the nitinol.
  • The method of making a stent may be described as follows. Age the shape memory material (Ni Ti) until body temperature falls somewhere within the transformation window. Therefore the stent will not fully recover to its high temperature shape at body temperature. An example of this technique is described below.
  • A stent of tubular 50.8% Ni balance Ti was prepared having a 1.5 mm diameter. It was substantially all austenite at room temperature, the Af being about 15-20° C. and therefore being superelastic at room temperature. The stent was cooled to below room temperature to form substantially all martensite and mechanically expanded to 4.7 mm in diameter. It was maintained at the 4.7 mm in diameter and heat treated at 500° C. for 30 minutes and water quenched. Finally, it was again cooled to below room temperature to form substantially all martensite and compressed to a diameter of 1.5 mm. After deployment and at body temperature the stent has a diameter of 3.5 mm. At about 70% of full expansion, i.e., about 40° C. it had a diameter of 4.5 mm and at 42° C. it had a fully expanded diameter of 4.7 mm.
  • This method works fairly well, but due to the slope of the temperature versus diameter plot being extremely vertical at body temperature, a small change in body temperature, or manufacturing control, can have a large impact on the actual self expansion diameter. As can be seen from FIG. 7, the slope of the line between Af and As is rather steep with small changes in temperature leading to large changes in percent austenite and consequently large changes in diameter of a stent made of such an alloy. FIG. 7 a shows a temperature versus diameter plot. Three methods of modifying the slope of the line on the temperature versus diameter graph are cold work, pseudoelastic prestraining, and amnesia inducement, illustrated in FIGS. 7 b, 7 c and 7 d, respectively.
  • Cold Work
  • Residual cold work in nitinol draws out or masks the point of Af on the diameter versus the temperature curve. This is seen by the sluggish increase in diameter as temperature increases in the last 20-30% of recover. By utilizing the effects of cold work, the effects of temperature change on diameter can be reduced in the last 20 to 30% of stent expansion. Shown in FIG. 7 b is an example of a temperature versus diameter plot for a cold worked part. FIG. 7 a above shows an example of a part without cold work.
  • Pseudoelastic Prestraining
  • Utilizing the effects of pseudoelastic prestraining (S. Eucken and T. W. Duerig, ACTA Metal, Vol. 37, No. 8, pp 2245-2252, 1989) one can create two distinct plateaus in the stress-strain behavior. This difference in stress strain behaviors can be directly linked to two distinct Af temperatures for the two plateaus. By placing the transition between the two plateaus at the transition from self expanding to balloon expanding, i.e., 70%, one can control the characteristics of the stent at body temperature. The goal would be to place the Af temperature for the first plateau (from maximum compression to 70% expansion) below body temperature such that the stent has self expanding characteristics. The Af temperature for the second plateau would be above body temperature such that there is no additional self expansion in this region (70 to 100% expansion) a mechanical device, like a balloon, can then be used to custom size the stent between 70% and 100% of the high temperature shape. Results of such a technique is shown in FIG. 7 c.
  • Amnesia Inducement
  • One of the characteristics of nitinol is cycle amnesia. This was also discussed about in the article referred to immediately above. As nitinol is cycled from its heat set shape as shown in FIG. 7 d, there is an increase in the amount of amnesia to recover to the heat set shape with each cycle. As long as this amnesia is not caused by permanent plastic deformation, the amnesia can be removed by heating the part above Md. This shows there is martensite left in the part after cycling which is preventing full recovery in the austenite phase (just above Af). This presence of non recoverable martensite (below Md) is what may be used for the balloon expansion region of the stent.
  • FIGS. 8-11 represent examples of various expandable configurations (a=closed, b=expanded) which may be incorporated into the devices of this invention. The version shown in FIGS. 10 a and 10 b may be modified as shown in FIGS. 10 c and 10 d (closed and open, respectively) by omitting portions (indicated at 100 in FIGS. 10 c and 10 d) as to render the stent flexible for articulation. This may be done to other of the structures as well to improve flexibility.
  • Yet another version of a device incorporating the two component concept of the invention is shown in FIG. 12. In this embodiment, a fragment of a stent 110 is shown. The stent includes a self-expanding component 112 and a deformable, external force expandable component 114. Self expanding component 112 may be resilient spring-like metal such a stainless steel or it may preferably be a shape memory alloy in the austenitic state. Component 114 may be any deformable metal or the like such as annealed stainless steel or preferably a shape memory alloy in the martensitic state. The two components may simply be mechanically, welded or bonded together. Functions and operations are as described hereinabove.
  • Referring to FIG. 13 a version analogous to the embodiment of FIG. 12 is shown in which the two component concept is again embodied as different zones or portions of a single metal material.
  • As shown in FIG. 13, a stent 120 (fragment showing) is of a self-expanding component 122 and a deformable component 124, both of which may be a single metal as spring steel or austenitic Ni—Ti which has been appropriately treated with respect to component 124 as by localized heat treatment or the like to alter the characteristics of the material of the 122 component so as to render it deformable or martensitic, depending on whether it is merely resilient or is austenitic. Again, function and operation are the same as with other embodiments.
  • Referring now to FIGS. 14-16, a multi-strand braided stent is shown in FIG. 15. Each strand 150 in the stent is a micro-cable. That is, each strand is made up of a plurality of wires 152 and 154 as is seen in FIGS. 15 and 16. Each of the wires 152 and 154 consists of two different nitinol alloys as seen best in FIG. 16, or one nitinol and one ordinary metal such as stainless steel, platinum or tantalum. The latter two would provide enhanced radiopacity. One nitinol alloy wire 154 has an austenitic finish (Af) temperature less than body temperature. The other wire 152 could be nitinol having an As (austenitic start) greater than body temperature. Also, it could be an ordinary metal. Additionally, one or more of the strands may be of a biodegradable material such as a plastic or may be of a material including an absorbable drug.
  • Since the two alloys are stranded into micro-cable one does not have to engage in selective, discrete heat treating methods to produce both shape memory and martensitic effects.
  • Radiopaque portions or coatings may be included on any parts of these stents as is known in the prior art.
  • While this invention may be embodied in many different forms, there are described in detail herein specific preferred embodiments of the invention. This description is an exemplification of the principles of the invention and is not intended to limit the invention to the particular embodiments illustrated.
  • The above Examples and disclosure are intended to be illustrative and not exhaustive. These examples and description will suggest many variations and alternatives to one of ordinary skill in this art. All these alternatives and variations are intended to be included within the scope of the attached claims. Those familiar with the art may recognize other equivalents to the specific embodiments described herein which equivalents are also intended to be encompassed by the claims attached hereto.

Claims (6)

1-34. (canceled)
35. A stent comprising:
a plurality of annular elements extending axially without engaging overlap, each annular element having a compressed state and an expanded state, wherein each annular element has a longitudinal dimension which is smaller in the radially expanded state than in the compressed state; and
at least one connecting member connecting adjacent of said annular elements, the connecting member having a longitudinal dimension and being configured to elongate the longitudinal dimension of the connecting member when the annular elements are transformed from the compressed state to the expanded state.
36. A tissue support device comprising:
a plurality of annular elements, each annular element having a compressed state and a radially expanded state, wherein each annular element has a longitudinal dimension which is smaller in the radially expanded state than in the compressed state; and
connecting members connecting adjacent of said annular elements, the connecting members having a longitudinal dimension and being configured so that the longitudinal dimension of the connecting members elongates longitudinally when the annular elements are transformed from the compressed state to the expanded state to compensate for the smaller longitudinal dimension of the annular elements in the expanded state.
37. A stent as in claim 36 wherein the connectors are U-shaped.
38. A stent as in claim 36 wherein the stent is formed of shape memory metal alloy material.
39-42. (canceled)
US10/443,231 1994-05-19 2003-05-21 Improved tissue supporting devices Abandoned US20110184508A2 (en)

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US09/172,590 US6451052B1 (en) 1994-05-19 1998-10-14 Tissue supporting devices
US09/427,291 US8221491B1 (en) 1994-05-19 1999-10-26 Tissue supporting devices
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Cited By (14)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US20060241690A1 (en) * 2004-03-19 2006-10-26 Aga Medical Corporation Multi-layer braided structures for occluding vascular defects and for occluding fluid flow through portions of the vasculature of the body
US20070265656A1 (en) * 2004-03-19 2007-11-15 Aga Medical Corporation Multi-layer braided structures for occluding vascular defects
US20080200945A1 (en) * 2004-03-19 2008-08-21 Aga Medical Corporation Device for occluding vascular defects
US20090062841A1 (en) * 2004-03-19 2009-03-05 Aga Medical Corporation Device for occluding vascular defects
US20090210048A1 (en) * 2008-02-18 2009-08-20 Aga Medical Corporation Stent/stent graft for reinforcement of vascular abnormalities and associated method
US20140277376A1 (en) * 2013-03-13 2014-09-18 DePuy Synthes Products, LLC Braid expansion ring with markers
US20180110636A1 (en) * 2016-10-21 2018-04-26 DePuy Synthes Products, Inc. Expansion ring for a braided stent
US10821008B2 (en) 2016-08-25 2020-11-03 DePuy Synthes Products, Inc. Expansion ring for a braided stent
US10821010B2 (en) 2014-08-27 2020-11-03 DePuy Synthes Products, Inc. Method of making a multi-strand implant with enhanced radiopacity
US11039944B2 (en) 2018-12-27 2021-06-22 DePuy Synthes Products, Inc. Braided stent system with one or more expansion rings
US11090175B2 (en) 2018-07-30 2021-08-17 DePuy Synthes Products, Inc. Systems and methods of manufacturing and using an expansion ring
US11129738B2 (en) 2016-09-30 2021-09-28 DePuy Synthes Products, Inc. Self-expanding device delivery apparatus with dual function bump
US11357648B2 (en) 2018-08-06 2022-06-14 DePuy Synthes Products, Inc. Systems and methods of using a braided implant
US11452623B2 (en) 2013-03-13 2022-09-27 DePuy Synthes Products, Inc. Braided stent with expansion ring and method of delivery

Families Citing this family (278)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
RU2089131C1 (en) * 1993-12-28 1997-09-10 Сергей Апполонович Пульнев Stent-expander
ATE166782T1 (en) 1994-02-25 1998-06-15 Fischell Robert STENT WITH A MULTIPLE CLOSED CIRCULAR STRUCTURES
US5733303A (en) * 1994-03-17 1998-03-31 Medinol Ltd. Flexible expandable stent
US6464722B2 (en) 1994-03-17 2002-10-15 Medinol, Ltd. Flexible expandable stent
US6461381B2 (en) 1994-03-17 2002-10-08 Medinol, Ltd. Flexible expandable stent
US5843120A (en) * 1994-03-17 1998-12-01 Medinol Ltd. Flexible-expandable stent
US5449373A (en) * 1994-03-17 1995-09-12 Medinol Ltd. Articulated stent
WO1995031945A1 (en) * 1994-05-19 1995-11-30 Scimed Life Systems, Inc. Improved tissue supporting devices
US5836964A (en) * 1996-10-30 1998-11-17 Medinol Ltd. Stent fabrication method
CA2134997C (en) * 1994-11-03 2009-06-02 Ian M. Penn Stent
ATE220308T1 (en) * 1995-03-01 2002-07-15 Scimed Life Systems Inc LONGITUDONLY FLEXIBLE AND EXPANDABLE STENT
US7204848B1 (en) 1995-03-01 2007-04-17 Boston Scientific Scimed, Inc. Longitudinally flexible expandable stent
US6818014B2 (en) 1995-03-01 2004-11-16 Scimed Life Systems, Inc. Longitudinally flexible expandable stent
DE19508805C2 (en) * 1995-03-06 2000-03-30 Lutz Freitag Stent for placement in a body tube with a flexible support structure made of at least two wires with different shape memory functions
US6264684B1 (en) 1995-03-10 2001-07-24 Impra, Inc., A Subsidiary Of C.R. Bard, Inc. Helically supported graft
US6451047B2 (en) * 1995-03-10 2002-09-17 Impra, Inc. Encapsulated intraluminal stent-graft and methods of making same
CZ292021B6 (en) 1995-04-26 2003-07-16 Medinol Ltd. Connector for connecting adjacent areas of adjacent segments of an articulated stent and the articulated stent per se
EP1669043A3 (en) * 1995-04-26 2006-06-28 Medinol Ltd. Articulated stent
DK171865B1 (en) * 1995-09-11 1997-07-21 Cook William Europ Expandable endovascular stent
US6689162B1 (en) * 1995-10-11 2004-02-10 Boston Scientific Scimed, Inc. Braided composite prosthesis
US5749848A (en) 1995-11-13 1998-05-12 Cardiovascular Imaging Systems, Inc. Catheter system having imaging, balloon angioplasty, and stent deployment capabilities, and method of use for guided stent deployment
US5843117A (en) * 1996-02-14 1998-12-01 Inflow Dynamics Inc. Implantable vascular and endoluminal stents and process of fabricating the same
WO1997032544A1 (en) * 1996-03-05 1997-09-12 Divysio Solutions Ulc. Expandable stent and method for delivery of same
CA2192520A1 (en) 1996-03-05 1997-09-05 Ian M. Penn Expandable stent and method for delivery of same
US6796997B1 (en) 1996-03-05 2004-09-28 Evysio Medical Devices Ulc Expandable stent
JP3815622B2 (en) * 1996-03-07 2006-08-30 エム イー ディー インスティチュート,インク Inflatable stent
JP4636634B2 (en) * 1996-04-26 2011-02-23 ボストン サイエンティフィック サイムド,インコーポレイテッド Intravascular stent
CA2204832A1 (en) * 1996-05-10 1997-11-10 Ann Eckert Expandable intraluminal graft or stent and method for implanting such an expandable intraluminal stent
US6007544A (en) * 1996-06-14 1999-12-28 Beth Israel Deaconess Medical Center Catheter apparatus having an improved shape-memory alloy cuff and inflatable on-demand balloon for creating a bypass graft in-vivo
US5800517A (en) * 1996-08-19 1998-09-01 Scimed Life Systems, Inc. Stent delivery system with storage sleeve
DE19633901A1 (en) * 1996-08-22 1998-02-26 Thomas Prof Dr Med Ischinger Vascular support in the form of a tube section-like support structure
US5807404A (en) 1996-09-19 1998-09-15 Medinol Ltd. Stent with variable features to optimize support and method of making such stent
US6036702A (en) * 1997-04-23 2000-03-14 Vascular Science Inc. Medical grafting connectors and fasteners
WO1998020810A1 (en) 1996-11-12 1998-05-22 Medtronic, Inc. Flexible, radially expansible luminal prostheses
US5906759A (en) 1996-12-26 1999-05-25 Medinol Ltd. Stent forming apparatus with stent deforming blades
BE1010858A4 (en) * 1997-01-16 1999-02-02 Medicorp R & D Benelux Sa Luminal endoprosthesis FOR BRANCHING.
CN1626048B (en) 1997-01-24 2012-09-12 帕拉贡知识产权有限责任公司 Expandable device having bistable spring construction
US8353948B2 (en) * 1997-01-24 2013-01-15 Celonova Stent, Inc. Fracture-resistant helical stent incorporating bistable cells and methods of use
US8663311B2 (en) 1997-01-24 2014-03-04 Celonova Stent, Inc. Device comprising biodegradable bistable or multistable cells and methods of use
US20040267350A1 (en) * 2002-10-30 2004-12-30 Roubin Gary S. Non-foreshortening intraluminal prosthesis
US5827321A (en) * 1997-02-07 1998-10-27 Cornerstone Devices, Inc. Non-Foreshortening intraluminal prosthesis
FR2760351B1 (en) 1997-03-04 1999-05-28 Bernard Glatt HELICAL STENT FORMING DEVICE AND MANUFACTURING METHOD THEREOF
US6159228A (en) * 1997-05-20 2000-12-12 Frid; Noureddine Applicator for luminal endoprostheses
BE1011180A6 (en) * 1997-05-27 1999-06-01 Medicorp R & D Benelux Sa Luminal endoprosthesis AUTO EXPANDABLE.
EP0884029B1 (en) 1997-06-13 2004-12-22 Gary J. Becker Expandable intraluminal endoprosthesis
NZ502727A (en) * 1997-07-08 2002-05-31 Novo Rps Ulc Expandable stent
DE29716117U1 (en) 1997-09-09 1999-01-14 Micro Science Medical Ag Stent
US6206910B1 (en) 1997-09-11 2001-03-27 Wake Forest University Compliant intraluminal stents
US6071308A (en) 1997-10-01 2000-06-06 Boston Scientific Corporation Flexible metal wire stent
US6342067B1 (en) 1998-01-09 2002-01-29 Nitinol Development Corporation Intravascular stent having curved bridges for connecting adjacent hoops
EP0945107A3 (en) * 1998-01-23 2000-01-19 Arterial Vascular Engineering, Inc. Helical stent
US6533807B2 (en) 1998-02-05 2003-03-18 Medtronic, Inc. Radially-expandable stent and delivery system
US6059809A (en) * 1998-02-16 2000-05-09 Medicorp, S.A. Protective angioplasty device
EP0943300A1 (en) * 1998-03-17 1999-09-22 Medicorp S.A. Reversible action endoprosthesis delivery device.
US6520983B1 (en) 1998-03-31 2003-02-18 Scimed Life Systems, Inc. Stent delivery system
US6019789A (en) * 1998-04-01 2000-02-01 Quanam Medical Corporation Expandable unit cell and intraluminal stent
US6264687B1 (en) * 1998-04-20 2001-07-24 Cordis Corporation Multi-laminate stent having superelastic articulated sections
EP0951870A1 (en) 1998-04-21 1999-10-27 Medicorp S.A. Device for aneurysma treatment
DE69935716T2 (en) 1998-05-05 2007-08-16 Boston Scientific Ltd., St. Michael STENT WITH SMOOTH ENDS
JP4378779B2 (en) 1998-07-17 2009-12-09 ダイキン工業株式会社 Method for producing fluorine-containing ethane
US6475234B1 (en) * 1998-10-26 2002-11-05 Medinol, Ltd. Balloon expandable covered stents
US7018401B1 (en) 1999-02-01 2006-03-28 Board Of Regents, The University Of Texas System Woven intravascular devices and methods for making the same and apparatus for delivery of the same
US6398803B1 (en) 1999-02-02 2002-06-04 Impra, Inc., A Subsidiary Of C.R. Bard, Inc. Partial encapsulation of stents
US6398802B1 (en) * 1999-06-21 2002-06-04 Scimed Life Systems, Inc. Low profile delivery system for stent and graft deployment
ES2243274T3 (en) 1999-07-02 2005-12-01 Endotex Interventional Systems, Inc. FLEXIBLE AND STRETCHABLE STENT SHAPED.
US6409754B1 (en) 1999-07-02 2002-06-25 Scimed Life Systems, Inc. Flexible segmented stent
US6485507B1 (en) 1999-07-28 2002-11-26 Scimed Life Systems Multi-property nitinol by heat treatment
US6890350B1 (en) * 1999-07-28 2005-05-10 Scimed Life Systems, Inc. Combination self-expandable, balloon-expandable endoluminal device
US6428569B1 (en) 1999-11-09 2002-08-06 Scimed Life Systems Inc. Micro structure stent configurations
US7226475B2 (en) 1999-11-09 2007-06-05 Boston Scientific Scimed, Inc. Stent with variable properties
US10172730B2 (en) * 1999-11-19 2019-01-08 Vactronix Scientific, Llc Stents with metallic covers and methods of making same
US7335426B2 (en) 1999-11-19 2008-02-26 Advanced Bio Prosthetic Surfaces, Ltd. High strength vacuum deposited nitinol alloy films and method of making same
US6676698B2 (en) * 2000-06-26 2004-01-13 Rex Medicol, L.P. Vascular device with valve for approximating vessel wall
US6695878B2 (en) * 2000-06-26 2004-02-24 Rex Medical, L.P. Vascular device for valve leaflet apposition
US6799637B2 (en) 2000-10-20 2004-10-05 Schlumberger Technology Corporation Expandable tubing and method
US6746461B2 (en) * 2000-08-15 2004-06-08 William R. Fry Low-profile, shape-memory surgical occluder
US7101391B2 (en) * 2000-09-18 2006-09-05 Inflow Dynamics Inc. Primarily niobium stent
US7402173B2 (en) * 2000-09-18 2008-07-22 Boston Scientific Scimed, Inc. Metal stent with surface layer of noble metal oxide and method of fabrication
US7037330B1 (en) * 2000-10-16 2006-05-02 Scimed Life Systems, Inc. Neurovascular stent and method
AU2001294738A1 (en) * 2000-10-31 2002-05-15 Scimed Life Systems, Inc. Endoluminal device having superelastic and plastically deformable sections
US7976648B1 (en) 2000-11-02 2011-07-12 Abbott Cardiovascular Systems Inc. Heat treatment for cold worked nitinol to impart a shape setting capability without eventually developing stress-induced martensite
US20100125329A1 (en) * 2000-11-02 2010-05-20 Zhi Cheng Lin Pseudoelastic stents having a drug coating and a method of producing the same
US6602272B2 (en) 2000-11-02 2003-08-05 Advanced Cardiovascular Systems, Inc. Devices configured from heat shaped, strain hardened nickel-titanium
US6626937B1 (en) * 2000-11-14 2003-09-30 Advanced Cardiovascular Systems, Inc. Austenitic nitinol medical devices
US8372139B2 (en) 2001-02-14 2013-02-12 Advanced Bio Prosthetic Surfaces, Ltd. In vivo sensor and method of making same
US20040098091A1 (en) * 2000-11-17 2004-05-20 Raimund Erbel Endovascular prosthesis
EP1341482B2 (en) 2000-12-11 2016-05-18 OrbusNeich Medical, Inc. Stent having helical elements
US7128757B2 (en) * 2000-12-27 2006-10-31 Advanced Cardiovascular, Inc. Radiopaque and MRI compatible nitinol alloys for medical devices
US6855161B2 (en) 2000-12-27 2005-02-15 Advanced Cardiovascular Systems, Inc. Radiopaque nitinol alloys for medical devices
US6569194B1 (en) 2000-12-28 2003-05-27 Advanced Cardiovascular Systems, Inc. Thermoelastic and superelastic Ni-Ti-W alloy
NO335594B1 (en) 2001-01-16 2015-01-12 Halliburton Energy Serv Inc Expandable devices and methods thereof
US6613077B2 (en) 2001-03-27 2003-09-02 Scimed Life Systems, Inc. Stent with controlled expansion
US6585753B2 (en) 2001-03-28 2003-07-01 Scimed Life Systems, Inc. Expandable coil stent
US7717708B2 (en) * 2001-04-13 2010-05-18 Orametrix, Inc. Method and system for integrated orthodontic treatment planning using unified workstation
US20050148925A1 (en) 2001-04-20 2005-07-07 Dan Rottenberg Device and method for controlling in-vivo pressure
EP1389975A4 (en) * 2001-04-26 2009-08-26 Vascular Innovation Inc Endoluminal device and method for fabricating same
US6551341B2 (en) * 2001-06-14 2003-04-22 Advanced Cardiovascular Systems, Inc. Devices configured from strain hardened Ni Ti tubing
DE10142998B4 (en) * 2001-09-03 2005-02-24 Stiftung Caesar Center Of Advanced European Studies And Research Shape memory composite with inherent motion sequence
US20030055485A1 (en) 2001-09-17 2003-03-20 Intra Therapeutics, Inc. Stent with offset cell geometry
DE60224950T2 (en) * 2001-12-03 2009-01-29 Intek Technology LLC, Wilmington MODULAR STENT COMPRISING MULTIPLE SEGMENTS AND METHOD FOR PRODUCING STENTS
US20040111147A1 (en) 2002-12-03 2004-06-10 Rabkin Dmitry J. Temporary, repositionable or retrievable intraluminal devices
US6945994B2 (en) * 2001-12-05 2005-09-20 Boston Scientific Scimed, Inc. Combined balloon-expanding and self-expanding stent
US20030163190A1 (en) * 2002-02-25 2003-08-28 Scimed Life Systems, Inc. High temperature stent delivery system
EP1507494A2 (en) * 2002-05-06 2005-02-23 Abbott Laboratories Endoprosthesis for controlled contraction and expansion
DE10233085B4 (en) 2002-07-19 2014-02-20 Dendron Gmbh Stent with guide wire
JP4995420B2 (en) * 2002-09-26 2012-08-08 アドヴァンスド バイオ プロスセティック サーフェシーズ リミテッド High strength vacuum deposited Nitinol alloy film, medical thin film graft material, and method of making same.
US6923829B2 (en) 2002-11-25 2005-08-02 Advanced Bio Prosthetic Surfaces, Ltd. Implantable expandable medical devices having regions of differential mechanical properties and methods of making same
DE10301850B4 (en) * 2003-01-16 2017-05-04 Dendron Gmbh stent
DE10362420B3 (en) * 2003-01-16 2020-10-29 Ussc Medical Gmbh Stent
US7399315B2 (en) * 2003-03-18 2008-07-15 Edwards Lifescience Corporation Minimally-invasive heart valve with cusp positioners
ATE467402T1 (en) 2003-03-26 2010-05-15 Cardiomind Inc IMPLANT DEPOSIT CATHETER WITH ELECTROLYTICALLY DEGRADABLE COMPOUNDS
US20040193178A1 (en) 2003-03-26 2004-09-30 Cardiomind, Inc. Multiple joint implant delivery systems for sequentially-controlled implant deployment
US7771463B2 (en) * 2003-03-26 2010-08-10 Ton Dai T Twist-down implant delivery technologies
US7942892B2 (en) 2003-05-01 2011-05-17 Abbott Cardiovascular Systems Inc. Radiopaque nitinol embolic protection frame
US7789979B2 (en) 2003-05-02 2010-09-07 Gore Enterprise Holdings, Inc. Shape memory alloy articles with improved fatigue performance and methods therefor
US20050004647A1 (en) * 2003-07-03 2005-01-06 William Cook Europe Aps Hybrid stent apparatus
US7455737B2 (en) * 2003-08-25 2008-11-25 Boston Scientific Scimed, Inc. Selective treatment of linear elastic materials to produce localized areas of superelasticity
US20060259137A1 (en) 2003-10-06 2006-11-16 Jason Artof Minimally invasive valve replacement system
WO2005044361A1 (en) 2003-11-07 2005-05-19 Merlin Md Pte Ltd Implantable medical devices with enhanced visibility, mechanical properties and biocompatibility
JP4351560B2 (en) * 2004-03-05 2009-10-28 Necトーキン株式会社 Balloon expandable superelastic stent
US8715340B2 (en) * 2004-03-31 2014-05-06 Merlin Md Pte Ltd. Endovascular device with membrane
US8500751B2 (en) 2004-03-31 2013-08-06 Merlin Md Pte Ltd Medical device
US8915952B2 (en) 2004-03-31 2014-12-23 Merlin Md Pte Ltd. Method for treating aneurysms
US7465318B2 (en) 2004-04-15 2008-12-16 Soteira, Inc. Cement-directing orthopedic implants
US7909873B2 (en) 2006-12-15 2011-03-22 Soteira, Inc. Delivery apparatus and methods for vertebrostenting
AU2005253930B2 (en) * 2004-05-11 2011-04-28 Oregon Health And Science University Interfacial stent and method of maintaining patency of surgical fenestrations
US8617234B2 (en) 2004-05-25 2013-12-31 Covidien Lp Flexible vascular occluding device
US20060206200A1 (en) 2004-05-25 2006-09-14 Chestnut Medical Technologies, Inc. Flexible vascular occluding device
US9675476B2 (en) * 2004-05-25 2017-06-13 Covidien Lp Vascular stenting for aneurysms
US8628564B2 (en) 2004-05-25 2014-01-14 Covidien Lp Methods and apparatus for luminal stenting
EP1750619B1 (en) 2004-05-25 2013-07-24 Covidien LP Flexible vascular occluding device
EP2419048A4 (en) 2004-05-25 2014-04-09 Covidien Lp Vascular stenting for aneurysms
US7641688B2 (en) 2004-09-16 2010-01-05 Evera Medical, Inc. Tissue augmentation device
WO2006034436A2 (en) 2004-09-21 2006-03-30 Stout Medical Group, L.P. Expandable support device and method of use
US7344560B2 (en) * 2004-10-08 2008-03-18 Boston Scientific Scimed, Inc. Medical devices and methods of making the same
US20070073380A1 (en) * 2004-12-20 2007-03-29 Vazquez Frank B Longitudinally expanding, rotating & contracting shaped memory superelastic stent
US8435280B2 (en) 2005-03-31 2013-05-07 Boston Scientific Scimed, Inc. Flexible stent with variable width elements
EP1903999B1 (en) 2005-04-25 2018-11-21 Covidien LP Controlled fracture connections for stents
JP5143342B2 (en) * 2005-05-23 2013-02-13 Necトーキン株式会社 Autonomous functional stent
JP4737518B2 (en) * 2005-05-23 2011-08-03 Necトーキン株式会社 Ti-Ni-Nb alloy element
US9162037B2 (en) 2005-07-06 2015-10-20 Vascular Pathways, Inc. Intravenous catheter insertion device and method of use
WO2007009107A2 (en) 2005-07-14 2007-01-18 Stout Medical Group, P.L. Expandable support device and method of use
WO2007013065A2 (en) 2005-07-25 2007-02-01 Rainbow Medical Ltd. Electrical stimulation of blood vessels
AU2012258286B2 (en) * 2005-08-31 2014-09-04 Advanced Bio Prosthetic Surfaces, Ltd., A Wholly Owned Subsidiary Of Palmaz Scientific, Inc. Covered stent with proximal and distal attachment, delivery catheter, and method of making same
US8187318B2 (en) * 2005-08-31 2012-05-29 Advanced Bio Prosthetic Surfaces, Ltd. Covered stent with proximal and distal attachment, delivery catheter, and method of making same
US20070100414A1 (en) 2005-11-02 2007-05-03 Cardiomind, Inc. Indirect-release electrolytic implant delivery systems
DE102005053393A1 (en) 2005-11-09 2007-05-10 Biotronik Vi Patent Ag Application system for a stent
WO2007083288A2 (en) 2006-01-23 2007-07-26 Atria Medical Inc. Heart anchor device
ES2375736T3 (en) * 2006-02-13 2012-03-05 Merlin Md Pte Ltd ENDOVASCULAR DEVICE WITH MEMBRANE.
WO2007100556A1 (en) 2006-02-22 2007-09-07 Ev3 Inc. Embolic protection systems having radiopaque filter mesh
EP2023864B1 (en) 2006-05-01 2019-07-10 Stout Medical Group, L.P. Expandable support device
US8690938B2 (en) 2006-05-26 2014-04-08 DePuy Synthes Products, LLC Occlusion device combination of stent and mesh with diamond-shaped porosity
US8118859B2 (en) 2006-05-26 2012-02-21 Codman & Shurtleff, Inc. Occlusion device combination of stent and mesh having offset parallelogram porosity
US9585743B2 (en) 2006-07-31 2017-03-07 Edwards Lifesciences Cardiaq Llc Surgical implant devices and methods for their manufacture and use
US9408607B2 (en) 2009-07-02 2016-08-09 Edwards Lifesciences Cardiaq Llc Surgical implant devices and methods for their manufacture and use
WO2008016578A2 (en) 2006-07-31 2008-02-07 Cartledge Richard G Sealable endovascular implants and methods for their use
US8728010B2 (en) * 2006-08-24 2014-05-20 Boston Scientific Scimed, Inc. Elongate medical device including deformable distal end
US7988720B2 (en) 2006-09-12 2011-08-02 Boston Scientific Scimed, Inc. Longitudinally flexible expandable stent
JP2010504174A (en) * 2006-09-21 2010-02-12 クレベニー テクノロジーズ Specially constructed and surface-modified medical devices with certain design features that take advantage of the unique properties of tungsten, zirconium, tantalum, and / or niobium
US7780798B2 (en) 2006-10-13 2010-08-24 Boston Scientific Scimed, Inc. Medical devices including hardened alloys
MX344492B (en) 2006-10-22 2016-12-16 Idev Tech Inc * Devices and methods for stent advancement.
EP3034046B1 (en) 2006-10-22 2018-01-17 IDEV Technologies, INC. Methods for securing strand ends and the resulting devices
US8191220B2 (en) 2006-12-04 2012-06-05 Cook Medical Technologies Llc Method for loading a medical device into a delivery system
US9480485B2 (en) 2006-12-15 2016-11-01 Globus Medical, Inc. Devices and methods for vertebrostenting
US8617205B2 (en) 2007-02-01 2013-12-31 Cook Medical Technologies Llc Closure device
WO2008094706A2 (en) 2007-02-01 2008-08-07 Cook Incorporated Closure device and method of closing a bodily opening
WO2008094691A2 (en) * 2007-02-01 2008-08-07 Cook Incorporated Closure device and method for occluding a bodily passageway
JP5139518B2 (en) 2007-05-07 2013-02-06 バスキュラー・パスウェイズ・インコーポレイテッド Venous catheter insertion device
WO2008148014A2 (en) * 2007-05-23 2008-12-04 C.R. Bard, Inc. Polymer coated stent
US9265636B2 (en) * 2007-05-25 2016-02-23 C. R. Bard, Inc. Twisted stent
US8211162B2 (en) * 2007-05-25 2012-07-03 Boston Scientific Scimed, Inc. Connector node for durable stent
US9814611B2 (en) 2007-07-31 2017-11-14 Edwards Lifesciences Cardiaq Llc Actively controllable stent, stent graft, heart valve and method of controlling same
US9566178B2 (en) 2010-06-24 2017-02-14 Edwards Lifesciences Cardiaq Llc Actively controllable stent, stent graft, heart valve and method of controlling same
US20090062838A1 (en) * 2007-08-27 2009-03-05 Cook Incorporated Spider device with occlusive barrier
US8734483B2 (en) * 2007-08-27 2014-05-27 Cook Medical Technologies Llc Spider PFO closure device
US8025495B2 (en) * 2007-08-27 2011-09-27 Cook Medical Technologies Llc Apparatus and method for making a spider occlusion device
US8308752B2 (en) * 2007-08-27 2012-11-13 Cook Medical Technologies Llc Barrel occlusion device
US8834551B2 (en) 2007-08-31 2014-09-16 Rex Medical, L.P. Vascular device with valve for approximating vessel wall
US8057532B2 (en) 2007-11-28 2011-11-15 Cook Medical Technologies Llc Implantable frame and valve design
WO2009073553A1 (en) 2007-11-30 2009-06-11 Cook Incorporated Method and device for vascular therapy
US9126023B1 (en) * 2007-12-14 2015-09-08 Gmedelaware 2 Llc Balloon expandable cement director and related methods
US8538535B2 (en) 2010-08-05 2013-09-17 Rainbow Medical Ltd. Enhancing perfusion by contraction
US20090198329A1 (en) 2008-02-01 2009-08-06 Kesten Randy J Breast implant with internal flow dampening
US8196279B2 (en) 2008-02-27 2012-06-12 C. R. Bard, Inc. Stent-graft covering process
US8267939B2 (en) 2008-02-28 2012-09-18 Stryker Spine Tool for implanting expandable intervertebral implant
AU2009236062A1 (en) 2008-04-18 2009-10-22 Cook Medical Technologies Llc Branched vessel prosthesis
ATE547071T1 (en) 2008-04-23 2012-03-15 Cook Medical Technologies Llc METHOD FOR INSERTING A MEDICAL DEVICE INTO A RELEASE SYSTEM
WO2009155319A1 (en) 2008-06-17 2009-12-23 Soteira, Inc. Devices and methods for fracture reduction
EP2318085B1 (en) * 2008-07-30 2020-03-11 Cornell University Apparatus for straightening and flattening the side wall of a body lumen or body cavity so as to provide three dimensional exposure of a lesion or abnormality within the body lumen or body cavity, and/or for stabilizing an instrument relative to the same
US8262692B2 (en) * 2008-09-05 2012-09-11 Merlin Md Pte Ltd Endovascular device
US8394138B2 (en) * 2008-09-05 2013-03-12 Cook Medical Technologies Llc Multi-strand helical stent
US8808294B2 (en) * 2008-09-09 2014-08-19 William Casey Fox Method and apparatus for a multiple transition temperature implant
EP2334258B1 (en) * 2008-09-12 2012-11-28 William A. Cook Australia Pty. Ltd. Radiopaque reinforcing member
US20100145433A1 (en) * 2008-09-30 2010-06-10 Abbott Cardiovascular Systems, Inc. Endoprostheses for deployment in a body lumen
US20100100170A1 (en) * 2008-10-22 2010-04-22 Boston Scientific Scimed, Inc. Shape memory tubular stent with grooves
WO2010051515A1 (en) 2008-10-31 2010-05-06 Fort Wayne Metals Research Products Corporation Method for imparting improved fatigue strength to wire made of shape memory alloys, and medical devices made from such wire
US20100211176A1 (en) 2008-11-12 2010-08-19 Stout Medical Group, L.P. Fixation device and method
US9408708B2 (en) 2008-11-12 2016-08-09 Stout Medical Group, L.P. Fixation device and method
GB2468861B (en) * 2009-03-23 2011-05-18 Cook William Europ Conformable stent structure and method of making same
US20210161637A1 (en) 2009-05-04 2021-06-03 V-Wave Ltd. Shunt for redistributing atrial blood volume
US8657870B2 (en) 2009-06-26 2014-02-25 Biosensors International Group, Ltd. Implant delivery apparatus and methods with electrolytic release
EP2453941B1 (en) 2009-07-13 2016-12-14 Cook Medical Technologies LLC Coated medical devices and methods
CN106901881B (en) 2009-10-30 2019-06-18 科迪斯公司 With improved flexible and durability intraluminal device
US8361140B2 (en) * 2009-12-29 2013-01-29 Boston Scientific Scimed, Inc. High strength low opening pressure stent design
US8353952B2 (en) 2010-04-07 2013-01-15 Medtronic Vascular, Inc. Stent with therapeutic substance
US10384039B2 (en) 2010-05-14 2019-08-20 C. R. Bard, Inc. Catheter insertion device including top-mounted advancement components
US9950139B2 (en) 2010-05-14 2018-04-24 C. R. Bard, Inc. Catheter placement device including guidewire and catheter control elements
US11925779B2 (en) 2010-05-14 2024-03-12 C. R. Bard, Inc. Catheter insertion device including top-mounted advancement components
US8932258B2 (en) 2010-05-14 2015-01-13 C. R. Bard, Inc. Catheter placement device and method
US9872971B2 (en) 2010-05-14 2018-01-23 C. R. Bard, Inc. Guidewire extension system for a catheter placement device
US9023095B2 (en) 2010-05-27 2015-05-05 Idev Technologies, Inc. Stent delivery system with pusher assembly
EP2422748B1 (en) * 2010-08-31 2016-01-27 Biotronik AG Medical implant, particularly valve implant, for implantation in an animal and/or human body and method, particularly production method, for producing an implantation apparatus for the medical implant
WO2012051489A2 (en) 2010-10-15 2012-04-19 Cook Medical Technologies Llc Occlusion device for blocking fluid flow through bodily passages
US9149286B1 (en) 2010-11-12 2015-10-06 Flexmedex, LLC Guidance tool and method for use
US8690833B2 (en) 2011-01-31 2014-04-08 Vascular Pathways, Inc. Intravenous catheter and insertion device with reduced blood spatter
EP2678065B1 (en) 2011-02-25 2019-09-11 C.R. Bard Inc. Medical component insertion device including a retractable needle
US8784474B2 (en) 2011-04-21 2014-07-22 Cook Medical Technologies Llc Emergency vascular repair system and method
USD903101S1 (en) 2011-05-13 2020-11-24 C. R. Bard, Inc. Catheter
EP2729092B1 (en) 2011-08-16 2016-09-21 Stryker European Holdings I, LLC Expandable implant
US9050112B2 (en) 2011-08-23 2015-06-09 Flexmedex, LLC Tissue removal device and method
US9526637B2 (en) 2011-09-09 2016-12-27 Enopace Biomedical Ltd. Wireless endovascular stent-based electrodes
US9827093B2 (en) 2011-10-21 2017-11-28 Edwards Lifesciences Cardiaq Llc Actively controllable stent, stent graft, heart valve and method of controlling same
US8894701B2 (en) * 2011-12-23 2014-11-25 Cook Medical Technologies Llc Hybrid balloon-expandable/self-expanding prosthesis for deployment in a body vessel and method of making
WO2013120082A1 (en) 2012-02-10 2013-08-15 Kassab Ghassan S Methods and uses of biological tissues for various stent and other medical applications
ES2943709T3 (en) 2012-04-06 2023-06-15 Merlin Md Pte Ltd Devices to treat an aneurysm
US9283069B2 (en) 2012-04-13 2016-03-15 Empire Technology Development Llc Intravitreous self adaptive stent
US9168122B2 (en) 2012-04-26 2015-10-27 Rex Medical, L.P. Vascular device and method for valve leaflet apposition
KR101231197B1 (en) * 2012-09-20 2013-02-07 썬텍 주식회사 Polymeric stent
US9301831B2 (en) 2012-10-30 2016-04-05 Covidien Lp Methods for attaining a predetermined porosity of a vascular device
US9452070B2 (en) 2012-10-31 2016-09-27 Covidien Lp Methods and systems for increasing a density of a region of a vascular device
US9943427B2 (en) 2012-11-06 2018-04-17 Covidien Lp Shaped occluding devices and methods of using the same
US9522254B2 (en) 2013-01-30 2016-12-20 Vascular Pathways, Inc. Systems and methods for venipuncture and catheter placement
US9157174B2 (en) 2013-02-05 2015-10-13 Covidien Lp Vascular device for aneurysm treatment and providing blood flow into a perforator vessel
AU2014214700B2 (en) 2013-02-11 2018-01-18 Cook Medical Technologies Llc Expandable support frame and medical device
US10342675B2 (en) 2013-03-11 2019-07-09 Stryker European Holdings I, Llc Expandable implant
US10905539B2 (en) 2013-03-15 2021-02-02 W. L. Gore & Associates, Inc. Self-expanding, balloon expandable stent-grafts
US9522072B2 (en) 2013-03-15 2016-12-20 W. L. Gore & Associates, Inc. Porous materials having a fibrillar microstructure and a fracturable coating
US9585695B2 (en) 2013-03-15 2017-03-07 Woven Orthopedic Technologies, Llc Surgical screw hole liner devices and related methods
EP2999412B1 (en) 2013-05-21 2020-05-06 V-Wave Ltd. Apparatus for delivering devices for reducing left atrial pressure
WO2014188437A2 (en) 2013-05-23 2014-11-27 S.T.S. Medical Ltd. Shape change structure
EP3065673A4 (en) 2013-11-06 2017-07-12 Enopace Biomedical Ltd. Wireless endovascular stent-based electrodes
US10214798B2 (en) 2013-11-15 2019-02-26 Massachussetts Institute Of Technology Method for controlling the energy damping of a shape memory alloy with surface roughness
US10188512B2 (en) 2013-12-30 2019-01-29 George O. Angheloiu Reversible cavitary tension membrane
US9668861B2 (en) 2014-03-15 2017-06-06 Rex Medical, L.P. Vascular device for treating venous valve insufficiency
US9907593B2 (en) 2014-08-05 2018-03-06 Woven Orthopedic Technologies, Llc Woven retention devices, systems and methods
US8956394B1 (en) 2014-08-05 2015-02-17 Woven Orthopedic Technologies, Llc Woven retention devices, systems and methods
US10232146B2 (en) 2014-09-05 2019-03-19 C. R. Bard, Inc. Catheter insertion device including retractable needle
US9943351B2 (en) 2014-09-16 2018-04-17 Woven Orthopedic Technologies, Llc Woven retention devices, systems, packaging, and related methods
CA2961664C (en) 2014-10-09 2020-04-14 Boston Scientific Scimed, Inc. Pancreatic stent with drainage feature
USD740427S1 (en) * 2014-10-17 2015-10-06 Woven Orthopedic Technologies, Llc Orthopedic woven retention device
US10912663B2 (en) 2014-11-26 2021-02-09 S.T.S. Medical Ltd. Shape change structure for treatment of nasal conditions including sinusitis
EP3282962B1 (en) * 2015-04-16 2019-10-16 Stryker Corporation Embolectomy devices
USD903100S1 (en) 2015-05-01 2020-11-24 C. R. Bard, Inc. Catheter placement device
CN107708769B (en) 2015-05-15 2021-07-27 C·R·巴德股份有限公司 Catheter placement device including extendable needle safety feature
US10555758B2 (en) 2015-08-05 2020-02-11 Woven Orthopedic Technologies, Llc Tapping devices, systems and methods for use in bone tissue
EP3362005B1 (en) * 2015-10-15 2020-12-16 Medical Development Technologies S.A. Improved implant device
US10835394B2 (en) 2016-05-31 2020-11-17 V-Wave, Ltd. Systems and methods for making encapsulated hourglass shaped stents
US20170340460A1 (en) 2016-05-31 2017-11-30 V-Wave Ltd. Systems and methods for making encapsulated hourglass shaped stents
US10426976B1 (en) * 2016-06-22 2019-10-01 The University Of Toledo Nitinol organ positioner to prevent damage to healthy tissue during radiation oncology treatments
CN112206397B (en) 2016-09-12 2023-03-21 C·R·巴德股份有限公司 Blood control of catheter insertion device
WO2018107114A1 (en) 2016-12-09 2018-06-14 Woven Orthopedic Technologies, LLC. Retention devices, lattices and related systems and methods
EP3585471A4 (en) 2017-03-01 2021-03-10 C.R. Bard, Inc. Catheter insertion device
US11291807B2 (en) 2017-03-03 2022-04-05 V-Wave Ltd. Asymmetric shunt for redistributing atrial blood volume
US10898698B1 (en) * 2020-05-04 2021-01-26 V-Wave Ltd. Devices with dimensions that can be reduced and increased in vivo, and methods of making and using the same
US11458287B2 (en) 2018-01-20 2022-10-04 V-Wave Ltd. Devices with dimensions that can be reduced and increased in vivo, and methods of making and using the same
US11744589B2 (en) 2018-01-20 2023-09-05 V-Wave Ltd. Devices and methods for providing passage between heart chambers
BR112020017215A2 (en) 2018-03-07 2020-12-22 Bard Access Systems, Inc. GUIDELINE ADVANCE SYSTEMS AND REVERSE BLOOD SQUEEZE FOR A MEDICAL DEVICE INSERT SYSTEM
US11291570B2 (en) 2018-04-27 2022-04-05 Cook Medical Technologies Llc Hybrid stent and delivery system
USD921884S1 (en) 2018-07-27 2021-06-08 Bard Access Systems, Inc. Catheter insertion device
JP7348292B2 (en) 2019-01-07 2023-09-20 ボストン サイエンティフィック サイムド,インコーポレイテッド Stent with anti-migration mechanism
US11612385B2 (en) 2019-04-03 2023-03-28 V-Wave Ltd. Systems and methods for delivering implantable devices across an atrial septum
WO2020234751A1 (en) 2019-05-20 2020-11-26 V-Wave Ltd. Systems and methods for creating an interatrial shunt
CN112386778A (en) 2019-08-19 2021-02-23 贝克顿·迪金森公司 Midline catheter placement device
CN111249044A (en) * 2020-03-20 2020-06-09 南微医学科技股份有限公司 Support and imbedding system
JP2023551927A (en) 2020-12-02 2023-12-13 ボストン サイエンティフィック サイムド,インコーポレイテッド Stents with improved deployment characteristics
US11400299B1 (en) 2021-09-14 2022-08-02 Rainbow Medical Ltd. Flexible antenna for stimulator
WO2023199267A1 (en) 2022-04-14 2023-10-19 V-Wave Ltd. Interatrial shunt with expanded neck region
US20230363914A1 (en) 2022-05-11 2023-11-16 Envveno Medical Corporation Transcatheter vein frame for venous insufficiency

Citations (97)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3174851A (en) * 1961-12-01 1965-03-23 William J Buehler Nickel-base alloys
US3585647A (en) * 1968-04-25 1971-06-22 Baxter Laboratories Inc Antithrombogenic article and process
US3657744A (en) * 1970-05-08 1972-04-25 Univ Minnesota Method for fixing prosthetic implants in a living body
US3808113A (en) * 1970-08-06 1974-04-30 Zaidan Hojin Seisan Kaihatsu K Method for manufacturing medical articles composed of various synthetic high polymers coated with collagen and exposed to radiation
US3868956A (en) * 1972-06-05 1975-03-04 Ralph J Alfidi Vessel implantable appliance and method of implanting it
US4030503A (en) * 1975-11-05 1977-06-21 Clark Iii William T Embolectomy catheter
US4140126A (en) * 1977-02-18 1979-02-20 Choudhury M Hasan Method for performing aneurysm repair
US4149911A (en) * 1977-01-24 1979-04-17 Raychem Limited Memory metal article
US4244140A (en) * 1977-11-14 1981-01-13 Kibong Kim Toys with shape memory alloys
US4313231A (en) * 1980-06-16 1982-02-02 Kabushiki Kaisha Tatebe Seishudo Vascular prosthesis
US4319363A (en) * 1978-05-23 1982-03-16 Vettivetpillai Ketharanathan Vascular prostheses
US4326532A (en) * 1980-10-06 1982-04-27 Minnesota Mining And Manufacturing Company Antithrombogenic articles
US4425908A (en) * 1981-10-22 1984-01-17 Beth Israel Hospital Blood clot filter
US4435853A (en) * 1982-04-30 1984-03-13 Hansa Medical Products, Inc. Voice prosthesis device and placement tool therefor
US4503569A (en) * 1983-03-03 1985-03-12 Dotter Charles T Transluminally placed expandable graft prosthesis
US4509517A (en) * 1982-09-30 1985-04-09 Zibelin Henry S Kidney stone instrument
US4512338A (en) * 1983-01-25 1985-04-23 Balko Alexander B Process for restoring patency to body vessels
US4572186A (en) * 1983-12-07 1986-02-25 Cordis Corporation Vessel dilation
US4577631A (en) * 1984-11-16 1986-03-25 Kreamer Jeffry W Aneurysm repair apparatus and method
US4580568A (en) * 1984-10-01 1986-04-08 Cook, Incorporated Percutaneous endovascular stent and method for insertion thereof
US4649922A (en) * 1986-01-23 1987-03-17 Wiktor Donimik M Catheter arrangement having a variable diameter tip and spring prosthesis
US4655771A (en) * 1982-04-30 1987-04-07 Shepherd Patents S.A. Prosthesis comprising an expansible or contractile tubular body
US4665906A (en) * 1983-10-14 1987-05-19 Raychem Corporation Medical devices incorporating sim alloy elements
US4665918A (en) * 1986-01-06 1987-05-19 Garza Gilbert A Prosthesis system and method
US4681110A (en) * 1985-12-02 1987-07-21 Wiktor Dominik M Catheter arrangement having a blood vessel liner, and method of using it
US4728322A (en) * 1986-02-05 1988-03-01 Menlo Care, Inc. Adjustable catheter assembly
US4729766A (en) * 1980-08-28 1988-03-08 Astra Meditec Aktiebolag Vascular prosthesis and method in producing it
US4732152A (en) * 1984-12-05 1988-03-22 Medinvent S.A. Device for implantation and a method of implantation in a vessel using such device
US4733665A (en) * 1985-11-07 1988-03-29 Expandable Grafts Partnership Expandable intraluminal graft, and method and apparatus for implanting an expandable intraluminal graft
US4740207A (en) * 1986-09-10 1988-04-26 Kreamer Jeffry W Intralumenal graft
US4795458A (en) * 1987-07-02 1989-01-03 Regan Barrie F Stent for use following balloon angioplasty
US4800882A (en) * 1987-03-13 1989-01-31 Cook Incorporated Endovascular stent and delivery system
US4817600A (en) * 1987-05-22 1989-04-04 Medi-Tech, Inc. Implantable filter
US4820298A (en) * 1987-11-20 1989-04-11 Leveen Eric G Internal vascular prosthesis
US4822361A (en) * 1985-12-24 1989-04-18 Sumitomo Electric Industries, Ltd. Tubular prosthesis having a composite structure
US4831094A (en) * 1982-09-20 1989-05-16 Societe Chimique Des Charbonnages, S.A. Articles having shape recovering properties and a method for using it
US4830003A (en) * 1988-06-17 1989-05-16 Wolff Rodney G Compressive stent and delivery system
US4832055A (en) * 1988-07-08 1989-05-23 Palestrant Aubrey M Mechanically locking blood clot filter
US4848343A (en) * 1986-10-31 1989-07-18 Medinvent S.A. Device for transluminal implantation
US4893623A (en) * 1986-12-09 1990-01-16 Advanced Surgical Intervention, Inc. Method and apparatus for treating hypertrophy of the prostate gland
US4911716A (en) * 1982-04-30 1990-03-27 Hansa Medical Products, Inc. Surgical implant for a voice prosthesis
US4911713A (en) * 1986-03-26 1990-03-27 Sauvage Lester R Method of making vascular prosthesis by perfusion
US4913141A (en) * 1988-10-25 1990-04-03 Cordis Corporation Apparatus and method for placement of a stent within a subject vessel
US4921484A (en) * 1988-07-25 1990-05-01 Cordis Corporation Mesh balloon catheter device
US4921499A (en) * 1987-10-05 1990-05-01 Ordev B.V. Adjustable prosthesis
US4922905A (en) * 1985-11-30 1990-05-08 Strecker Ernst P Dilatation catheter
US4926860A (en) * 1988-02-05 1990-05-22 Flexmedics Corporation ARthroscopic instrumentation and method
US4934380A (en) * 1987-11-27 1990-06-19 Boston Scientific Corporation Medical guidewire
US4990155A (en) * 1989-05-19 1991-02-05 Wilkoff Howard M Surgical stent method and apparatus
US4994069A (en) * 1988-11-02 1991-02-19 Target Therapeutics Vaso-occlusion coil and method
US4994071A (en) * 1989-05-22 1991-02-19 Cordis Corporation Bifurcating stent apparatus and method
US4998923A (en) * 1988-08-11 1991-03-12 Advanced Cardiovascular Systems, Inc. Steerable dilatation catheter
US5003989A (en) * 1989-05-11 1991-04-02 Advanced Cardiovascular Systems, Inc. Steerable dilation catheter
US5019090A (en) * 1988-09-01 1991-05-28 Corvita Corporation Radially expandable endoprosthesis and the like
US5035712A (en) * 1989-06-16 1991-07-30 Ordev B.V. Self-adjusting prosthesis attachment
US5078736A (en) * 1990-05-04 1992-01-07 Interventional Thermodynamics, Inc. Method and apparatus for maintaining patency in the body passages
US5078726A (en) * 1989-02-01 1992-01-07 Kreamer Jeffry W Graft stent and method of repairing blood vessels
US5100429A (en) * 1989-04-28 1992-03-31 C. R. Bard, Inc. Endovascular stent and delivery system
US5102417A (en) * 1985-11-07 1992-04-07 Expandable Grafts Partnership Expandable intraluminal graft, and method and apparatus for implanting an expandable intraluminal graft
US5104404A (en) * 1989-10-02 1992-04-14 Medtronic, Inc. Articulated stent
US5108420A (en) * 1991-02-01 1992-04-28 Temple University Aperture occlusion device
US5123917A (en) * 1990-04-27 1992-06-23 Lee Peter Y Expandable intraluminal vascular graft
US5129883A (en) * 1990-07-26 1992-07-14 Michael Black Catheter
US5176664A (en) * 1990-10-09 1993-01-05 Kenneth Weisman Female voiding assist device and method
US5183085A (en) * 1991-09-27 1993-02-02 Hans Timmermans Method and apparatus for compressing a stent prior to insertion
US5189110A (en) * 1988-12-23 1993-02-23 Asahi Kasei Kogyo Kabushiki Kaisha Shape memory polymer resin, composition and the shape memorizing molded product thereof
US5190546A (en) * 1983-10-14 1993-03-02 Raychem Corporation Medical devices incorporating SIM alloy elements
US5195984A (en) * 1988-10-04 1993-03-23 Expandable Grafts Partnership Expandable intraluminal graft
US5197978A (en) * 1991-04-26 1993-03-30 Advanced Coronary Technology, Inc. Removable heat-recoverable tissue supporting device
US5201901A (en) * 1987-10-08 1993-04-13 Terumo Kabushiki Kaisha Expansion unit and apparatus for expanding tubular organ lumen
US5211658A (en) * 1991-11-05 1993-05-18 New England Deaconess Hospital Corporation Method and device for performing endovascular repair of aneurysms
US5217483A (en) * 1990-11-28 1993-06-08 Numed, Inc. Intravascular radially expandable stent
US5275622A (en) * 1983-12-09 1994-01-04 Harrison Medical Technologies, Inc. Endovascular grafting apparatus, system and method and devices for use therewith
US5282824A (en) * 1990-10-09 1994-02-01 Cook, Incorporated Percutaneous stent assembly
US5292331A (en) * 1989-08-24 1994-03-08 Applied Vascular Engineering, Inc. Endovascular support device
US5304200A (en) * 1991-05-29 1994-04-19 Cordis Corporation Welded radially expandable endoprosthesis and the like
US5314472A (en) * 1991-10-01 1994-05-24 Cook Incorporated Vascular stent
US5383892A (en) * 1991-11-08 1995-01-24 Meadox France Stent for transluminal implantation
US5601593A (en) * 1995-03-06 1997-02-11 Willy Rusch Ag Stent for placement in a body tube
US5609605A (en) * 1994-08-25 1997-03-11 Ethicon, Inc. Combination arterial stent
US5707387A (en) * 1996-03-25 1998-01-13 Wijay; Bandula Flexible stent
US5733303A (en) * 1994-03-17 1998-03-31 Medinol Ltd. Flexible expandable stent
US5735871A (en) * 1994-12-09 1998-04-07 Sgro; Jean-Claude Self-expanding endoprosthesis
US5749825A (en) * 1996-09-18 1998-05-12 Isostent, Inc. Means method for treatment of stenosed arterial bifurcations
US5755772A (en) * 1995-03-31 1998-05-26 Medtronic, Inc. Radially expansible vascular prosthesis having reversible and other locking structures
US5879370A (en) * 1994-02-25 1999-03-09 Fischell; Robert E. Stent having a multiplicity of undulating longitudinals
US5888201A (en) * 1996-02-08 1999-03-30 Schneider (Usa) Inc Titanium alloy self-expanding stent
US5913895A (en) * 1997-06-02 1999-06-22 Isostent, Inc. Intravascular stent with enhanced rigidity strut members
US5916234A (en) * 1993-12-28 1999-06-29 Advanced Cardiovascular Systems, Inc. Expandable stents and method for making same
US6051021A (en) * 1997-05-27 2000-04-18 Medicorp, S.A. Self-expanding endoprosthesis
US6245100B1 (en) * 2000-02-01 2001-06-12 Cordis Corporation Method for making a self-expanding stent-graft
US6251134B1 (en) * 1999-02-28 2001-06-26 Inflow Dynamics Inc. Stent with high longitudinal flexibility
US6348065B1 (en) * 1995-03-01 2002-02-19 Scimed Life Systems, Inc. Longitudinally flexible expandable stent
US6517547B1 (en) * 1999-09-07 2003-02-11 Angiomed Gmbh & Co. Medizintechnik Kg Stent delivery system
US6562063B1 (en) * 1993-10-22 2003-05-13 Scimed Life Systems, Inc. Stent delivery apparatus and method
US6562067B2 (en) * 2001-06-08 2003-05-13 Cordis Corporation Stent with interlocking elements
US20070150049A1 (en) * 2004-03-16 2007-06-28 Alveolus, Inc. Stent

Family Cites Families (87)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3012883A (en) 1959-07-09 1961-12-12 Nat Res Corp Niobium base alloy
GB1491202A (en) 1973-10-17 1977-11-09 Warne Surgical Products Ltd Catheter or tube having a tip which is high in opacity to x-rays
US3923065A (en) 1974-09-09 1975-12-02 Jerome Nozick Embolectomy catheter
US4046150A (en) 1975-07-17 1977-09-06 American Hospital Supply Corporation Medical instrument for locating and removing occlusive objects
US4170990A (en) 1977-01-28 1979-10-16 Fried. Krupp Gesellschaft Mit Beschrankter Haftung Method for implanting and subsequently removing mechanical connecting elements from living tissue
JPS5563278A (en) 1978-11-02 1980-05-13 Ricoh Co Ltd Multi-head ink jet recorder
JPS6037734B2 (en) 1978-10-12 1985-08-28 住友電気工業株式会社 Tubular organ prosthesis material and its manufacturing method
US4300244A (en) 1979-09-19 1981-11-17 Carbomedics, Inc. Cardiovascular grafts
IT1126526B (en) 1979-12-07 1986-05-21 Enrico Dormia SURGICAL EXTRACTOR TO REMOVE FOREIGN BODIES THAT ARE FOUND IN THE NATURAL ROUTES OF THE HUMAN BODY, AS CALCULATIONS AND SIMILAR
JPH0121984B2 (en) 1980-07-01 1989-04-24 Betsuteibetopirai Kesaranazan
DE3250058C2 (en) 1981-09-16 1992-08-27 Medinvent S.A., Lausanne, Ch
US4614516A (en) 1982-04-30 1986-09-30 Hansa Medical Products, Inc. Voice prosthesis device
CH651462A5 (en) 1983-02-23 1985-09-30 Helmut Hader FEMALE PART OF A COUPLING FOR MOUTH FIXING OF A DENTAL PROSTHESIS.
US5067957A (en) 1983-10-14 1991-11-26 Raychem Corporation Method of inserting medical devices incorporating SIM alloy elements
US4560374A (en) 1983-10-17 1985-12-24 Hammerslag Julius G Method for repairing stenotic vessels
EP0183372A1 (en) * 1984-10-19 1986-06-04 RAYCHEM CORPORATION (a Delaware corporation) Prosthetic stent
DE3583399D1 (en) 1984-11-09 1991-08-08 Implanto Lock Gmbh Fuer Implan ENOSSAL IMPLANT FOR FIXING FIXED OR REMOVABLE DENTAL REPLACEMENT.
GB2175824A (en) * 1985-05-29 1986-12-10 Barry Rene Christopher Paul Producing composite metal articles
US4955863A (en) 1986-02-05 1990-09-11 Menlo Care, Inc. Adjustable catheter assembly
EP0257091B1 (en) 1986-02-24 1993-07-28 Robert E. Fischell An intravascular stent and percutaneous insertion system
US4878906A (en) 1986-03-25 1989-11-07 Servetus Partnership Endoprosthesis for repairing a damaged vessel
SE453258B (en) 1986-04-21 1988-01-25 Medinvent Sa ELASTIC, SELF-EXPANDING PROTEST AND PROCEDURE FOR ITS MANUFACTURING
US4762128A (en) 1986-12-09 1988-08-09 Advanced Surgical Intervention, Inc. Method and apparatus for treating hypertrophy of the prostate gland
US5041126A (en) 1987-03-13 1991-08-20 Cook Incorporated Endovascular stent and delivery system
JPS63238872A (en) 1987-03-25 1988-10-04 テルモ株式会社 Instrument for securing inner diameter of cavity of tubular organ and catheter equipped therewith
US5059211A (en) 1987-06-25 1991-10-22 Duke University Absorbable vascular stent
US4969458A (en) 1987-07-06 1990-11-13 Medtronic, Inc. Intracoronary stent and method of simultaneous angioplasty and stent implant
JPH088933B2 (en) 1987-07-10 1996-01-31 日本ゼオン株式会社 Catheter
JPS6446477A (en) 1987-08-13 1989-02-20 Terumo Corp Catheter
US5242451A (en) 1987-09-24 1993-09-07 Terumo Kabushiki Kaisha Instrument for retaining inner diameter of tubular organ lumen
JPS6483251A (en) 1987-09-24 1989-03-29 Terumo Corp Instrument for securing inner diameter of cavity of tubular organ
US5133732A (en) 1987-10-19 1992-07-28 Medtronic, Inc. Intravascular stent
US4886062A (en) 1987-10-19 1989-12-12 Medtronic, Inc. Intravascular radially expandable stent and method of implant
JP2561853B2 (en) 1988-01-28 1996-12-11 株式会社ジェイ・エム・エス Shaped memory molded article and method of using the same
US4919133A (en) * 1988-08-18 1990-04-24 Chiang Tien Hon Catheter apparatus employing shape memory alloy structures
JP2740867B2 (en) * 1988-10-07 1998-04-15 バリー・エフ・リーガン Stent and its manufacturing method
US4856516A (en) 1989-01-09 1989-08-15 Cordis Corporation Endovascular stent apparatus and method
US5234425A (en) * 1989-03-03 1993-08-10 Thomas J. Fogarty Variable diameter sheath method and apparatus for use in body passages
US4955384A (en) 1989-05-11 1990-09-11 Advanced Cardiovascular Systems, Inc. Guiding member for vascular catheters with a flexible link distal section
US5019040A (en) * 1989-08-31 1991-05-28 Koshin Sangyo Kabushiki Kaisha Catheter
US5057092A (en) 1990-04-04 1991-10-15 Webster Wilton W Jr Braided catheter with low modulus warp
US5071407A (en) 1990-04-12 1991-12-10 Schneider (U.S.A.) Inc. Radially expandable fixation member
IL94138A (en) 1990-04-19 1997-03-18 Instent Inc Device for the treatment of constricted fluid conducting ducts
US5242399A (en) 1990-04-25 1993-09-07 Advanced Cardiovascular Systems, Inc. Method and system for stent delivery
EP0461791B1 (en) 1990-06-11 1997-01-02 Hector D. Barone Aortic graft and apparatus for repairing an abdominal aortic aneurysm
US5360443A (en) 1990-06-11 1994-11-01 Barone Hector D Aortic graft for repairing an abdominal aortic aneurysm
US5064435A (en) 1990-06-28 1991-11-12 Schneider (Usa) Inc. Self-expanding prosthesis having stable axial length
US5171314A (en) 1990-07-24 1992-12-15 Andrew Surgical, Inc. Surgical snare
US5064428A (en) 1990-09-18 1991-11-12 Cook Incorporated Medical retrieval basket
US5057114A (en) 1990-09-18 1991-10-15 Cook Incorporated Medical retrieval basket
DE69121592T2 (en) * 1991-01-04 1997-01-02 American Med Syst RESPECTABLE SELF-SPREADING STENT
US5135536A (en) 1991-02-05 1992-08-04 Cordis Corporation Endovascular stent and method
US5231989A (en) 1991-02-15 1993-08-03 Raychem Corporation Steerable cannula
CA2065634C (en) 1991-04-11 1997-06-03 Alec A. Piplani Endovascular graft having bifurcation and apparatus and method for deploying the same
US5241970A (en) 1991-05-17 1993-09-07 Wilson-Cook Medical, Inc. Papillotome/sphincterotome procedures and a wire guide specially
US5154725A (en) 1991-06-07 1992-10-13 Advanced Cardiovascular Systems, Inc. Easily exchangeable catheter system
US5147370A (en) * 1991-06-12 1992-09-15 Mcnamara Thomas O Nitinol stent for hollow body conduits
US5242448A (en) 1991-08-01 1993-09-07 Pettine Kenneth A Bone probe
US5366504A (en) * 1992-05-20 1994-11-22 Boston Scientific Corporation Tubular medical prosthesis
US5354309A (en) 1991-10-11 1994-10-11 Angiomed Ag Apparatus for widening a stenosis in a body cavity
US5167614A (en) 1991-10-29 1992-12-01 Medical Engineering Corporation Prostatic stent
US5238005A (en) 1991-11-18 1993-08-24 Intelliwire, Inc. Steerable catheter guidewire
US5256150A (en) 1991-12-13 1993-10-26 Endovascular Technologies, Inc. Large-diameter expandable sheath and method
CA2087132A1 (en) 1992-01-31 1993-08-01 Michael S. Williams Stent capable of attachment within a body lumen
US5405377A (en) 1992-02-21 1995-04-11 Endotech Ltd. Intraluminal stent
US5282823A (en) 1992-03-19 1994-02-01 Medtronic, Inc. Intravascular radially expandable stent
ES2116406T3 (en) 1992-03-25 1998-07-16 Cook Inc STENT VASCULAR.
JP3118077B2 (en) 1992-04-20 2000-12-18 株式会社ソフィア Ball ejection device of pachinko machine
US5224953A (en) 1992-05-01 1993-07-06 The Beth Israel Hospital Association Method for treatment of obstructive portions of urinary passageways
US5354308A (en) 1992-05-01 1994-10-11 Beth Israel Hospital Association Metal wire stent
US5261878A (en) 1992-05-19 1993-11-16 The Regents Of The University Of California Double balloon pediatric ductus arteriosus stent catheter and method of using the same
HU217926B (en) * 1992-08-06 2000-05-28 William Cook Europe A/S A prosthetic device for sustaining a blood-vessels or hollow organs lumen
US5423849A (en) * 1993-01-15 1995-06-13 Target Therapeutics, Inc. Vasoocclusion device containing radiopaque fibers
IL105828A (en) 1993-05-28 1999-06-20 Medinol Ltd Medical stent
US5464449A (en) * 1993-07-08 1995-11-07 Thomas J. Fogarty Internal graft prosthesis and delivery system
US5609627A (en) * 1994-02-09 1997-03-11 Boston Scientific Technology, Inc. Method for delivering a bifurcated endoluminal prosthesis
US6051020A (en) * 1994-02-09 2000-04-18 Boston Scientific Technology, Inc. Bifurcated endoluminal prosthesis
US5643312A (en) 1994-02-25 1997-07-01 Fischell Robert Stent having a multiplicity of closed circular structures
US5449373A (en) * 1994-03-17 1995-09-12 Medinol Ltd. Articulated stent
US5478349A (en) * 1994-04-28 1995-12-26 Boston Scientific Corporation Placement of endoprostheses and stents
WO1995031945A1 (en) * 1994-05-19 1995-11-30 Scimed Life Systems, Inc. Improved tissue supporting devices
US5575817A (en) * 1994-08-19 1996-11-19 Martin; Eric C. Aorto femoral bifurcation graft and method of implantation
US6102929A (en) * 1994-09-15 2000-08-15 Mentor Urology, Inc. Prostatic tissue expander
US5545210A (en) 1994-09-22 1996-08-13 Advanced Coronary Technology, Inc. Method of implanting a permanent shape memory alloy stent
US5674277A (en) 1994-12-23 1997-10-07 Willy Rusch Ag Stent for placement in a body tube
US6152957A (en) 1996-04-26 2000-11-28 Jang; G. David Intravascular stent
US5827321A (en) * 1997-02-07 1998-10-27 Cornerstone Devices, Inc. Non-Foreshortening intraluminal prosthesis

Patent Citations (104)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US3174851A (en) * 1961-12-01 1965-03-23 William J Buehler Nickel-base alloys
US3585647A (en) * 1968-04-25 1971-06-22 Baxter Laboratories Inc Antithrombogenic article and process
US3657744A (en) * 1970-05-08 1972-04-25 Univ Minnesota Method for fixing prosthetic implants in a living body
US3808113A (en) * 1970-08-06 1974-04-30 Zaidan Hojin Seisan Kaihatsu K Method for manufacturing medical articles composed of various synthetic high polymers coated with collagen and exposed to radiation
US3868956A (en) * 1972-06-05 1975-03-04 Ralph J Alfidi Vessel implantable appliance and method of implanting it
US4030503A (en) * 1975-11-05 1977-06-21 Clark Iii William T Embolectomy catheter
US4149911A (en) * 1977-01-24 1979-04-17 Raychem Limited Memory metal article
US4140126A (en) * 1977-02-18 1979-02-20 Choudhury M Hasan Method for performing aneurysm repair
US4244140A (en) * 1977-11-14 1981-01-13 Kibong Kim Toys with shape memory alloys
US4319363A (en) * 1978-05-23 1982-03-16 Vettivetpillai Ketharanathan Vascular prostheses
US4313231A (en) * 1980-06-16 1982-02-02 Kabushiki Kaisha Tatebe Seishudo Vascular prosthesis
US4729766A (en) * 1980-08-28 1988-03-08 Astra Meditec Aktiebolag Vascular prosthesis and method in producing it
US4326532A (en) * 1980-10-06 1982-04-27 Minnesota Mining And Manufacturing Company Antithrombogenic articles
US4425908A (en) * 1981-10-22 1984-01-17 Beth Israel Hospital Blood clot filter
US4435853A (en) * 1982-04-30 1984-03-13 Hansa Medical Products, Inc. Voice prosthesis device and placement tool therefor
US4911716A (en) * 1982-04-30 1990-03-27 Hansa Medical Products, Inc. Surgical implant for a voice prosthesis
US4655771B1 (en) * 1982-04-30 1996-09-10 Medinvent Ams Sa Prosthesis comprising an expansible or contractile tubular body
US4655771A (en) * 1982-04-30 1987-04-07 Shepherd Patents S.A. Prosthesis comprising an expansible or contractile tubular body
US4831094A (en) * 1982-09-20 1989-05-16 Societe Chimique Des Charbonnages, S.A. Articles having shape recovering properties and a method for using it
US4509517A (en) * 1982-09-30 1985-04-09 Zibelin Henry S Kidney stone instrument
US4512338A (en) * 1983-01-25 1985-04-23 Balko Alexander B Process for restoring patency to body vessels
US4503569A (en) * 1983-03-03 1985-03-12 Dotter Charles T Transluminally placed expandable graft prosthesis
US4665906A (en) * 1983-10-14 1987-05-19 Raychem Corporation Medical devices incorporating sim alloy elements
US5190546A (en) * 1983-10-14 1993-03-02 Raychem Corporation Medical devices incorporating SIM alloy elements
US4572186A (en) * 1983-12-07 1986-02-25 Cordis Corporation Vessel dilation
US5275622A (en) * 1983-12-09 1994-01-04 Harrison Medical Technologies, Inc. Endovascular grafting apparatus, system and method and devices for use therewith
US4580568A (en) * 1984-10-01 1986-04-08 Cook, Incorporated Percutaneous endovascular stent and method for insertion thereof
US4577631A (en) * 1984-11-16 1986-03-25 Kreamer Jeffry W Aneurysm repair apparatus and method
US4732152A (en) * 1984-12-05 1988-03-22 Medinvent S.A. Device for implantation and a method of implantation in a vessel using such device
US4733665B1 (en) * 1985-11-07 1994-01-11 Expandable Grafts Partnership Expandable intraluminal graft,and method and apparatus for implanting an expandable intraluminal graft
US4733665A (en) * 1985-11-07 1988-03-29 Expandable Grafts Partnership Expandable intraluminal graft, and method and apparatus for implanting an expandable intraluminal graft
US4733665C2 (en) * 1985-11-07 2002-01-29 Expandable Grafts Partnership Expandable intraluminal graft and method and apparatus for implanting an expandable intraluminal graft
US4739762A (en) * 1985-11-07 1988-04-26 Expandable Grafts Partnership Expandable intraluminal graft, and method and apparatus for implanting an expandable intraluminal graft
US4739762B1 (en) * 1985-11-07 1998-10-27 Expandable Grafts Partnership Expandable intraluminal graft and method and apparatus for implanting an expandable intraluminal graft
US5102417A (en) * 1985-11-07 1992-04-07 Expandable Grafts Partnership Expandable intraluminal graft, and method and apparatus for implanting an expandable intraluminal graft
US4922905A (en) * 1985-11-30 1990-05-08 Strecker Ernst P Dilatation catheter
US4681110A (en) * 1985-12-02 1987-07-21 Wiktor Dominik M Catheter arrangement having a blood vessel liner, and method of using it
US4822361A (en) * 1985-12-24 1989-04-18 Sumitomo Electric Industries, Ltd. Tubular prosthesis having a composite structure
US4665918A (en) * 1986-01-06 1987-05-19 Garza Gilbert A Prosthesis system and method
US4649922A (en) * 1986-01-23 1987-03-17 Wiktor Donimik M Catheter arrangement having a variable diameter tip and spring prosthesis
US4728322A (en) * 1986-02-05 1988-03-01 Menlo Care, Inc. Adjustable catheter assembly
US4911713A (en) * 1986-03-26 1990-03-27 Sauvage Lester R Method of making vascular prosthesis by perfusion
US4740207A (en) * 1986-09-10 1988-04-26 Kreamer Jeffry W Intralumenal graft
US4848343A (en) * 1986-10-31 1989-07-18 Medinvent S.A. Device for transluminal implantation
US4893623A (en) * 1986-12-09 1990-01-16 Advanced Surgical Intervention, Inc. Method and apparatus for treating hypertrophy of the prostate gland
US4800882A (en) * 1987-03-13 1989-01-31 Cook Incorporated Endovascular stent and delivery system
US4817600A (en) * 1987-05-22 1989-04-04 Medi-Tech, Inc. Implantable filter
US4795458A (en) * 1987-07-02 1989-01-03 Regan Barrie F Stent for use following balloon angioplasty
US4921499A (en) * 1987-10-05 1990-05-01 Ordev B.V. Adjustable prosthesis
US5201901A (en) * 1987-10-08 1993-04-13 Terumo Kabushiki Kaisha Expansion unit and apparatus for expanding tubular organ lumen
US4820298A (en) * 1987-11-20 1989-04-11 Leveen Eric G Internal vascular prosthesis
US4934380A (en) * 1987-11-27 1990-06-19 Boston Scientific Corporation Medical guidewire
US4926860A (en) * 1988-02-05 1990-05-22 Flexmedics Corporation ARthroscopic instrumentation and method
US4830003A (en) * 1988-06-17 1989-05-16 Wolff Rodney G Compressive stent and delivery system
US4832055A (en) * 1988-07-08 1989-05-23 Palestrant Aubrey M Mechanically locking blood clot filter
US4921484A (en) * 1988-07-25 1990-05-01 Cordis Corporation Mesh balloon catheter device
US4998923A (en) * 1988-08-11 1991-03-12 Advanced Cardiovascular Systems, Inc. Steerable dilatation catheter
US5019090A (en) * 1988-09-01 1991-05-28 Corvita Corporation Radially expandable endoprosthesis and the like
US5195984A (en) * 1988-10-04 1993-03-23 Expandable Grafts Partnership Expandable intraluminal graft
US4913141A (en) * 1988-10-25 1990-04-03 Cordis Corporation Apparatus and method for placement of a stent within a subject vessel
US4994069A (en) * 1988-11-02 1991-02-19 Target Therapeutics Vaso-occlusion coil and method
US5189110A (en) * 1988-12-23 1993-02-23 Asahi Kasei Kogyo Kabushiki Kaisha Shape memory polymer resin, composition and the shape memorizing molded product thereof
US5078726A (en) * 1989-02-01 1992-01-07 Kreamer Jeffry W Graft stent and method of repairing blood vessels
US5100429A (en) * 1989-04-28 1992-03-31 C. R. Bard, Inc. Endovascular stent and delivery system
US5003989A (en) * 1989-05-11 1991-04-02 Advanced Cardiovascular Systems, Inc. Steerable dilation catheter
US4990155A (en) * 1989-05-19 1991-02-05 Wilkoff Howard M Surgical stent method and apparatus
US4994071A (en) * 1989-05-22 1991-02-19 Cordis Corporation Bifurcating stent apparatus and method
US5035712A (en) * 1989-06-16 1991-07-30 Ordev B.V. Self-adjusting prosthesis attachment
US5292331A (en) * 1989-08-24 1994-03-08 Applied Vascular Engineering, Inc. Endovascular support device
US5104404A (en) * 1989-10-02 1992-04-14 Medtronic, Inc. Articulated stent
US5123917A (en) * 1990-04-27 1992-06-23 Lee Peter Y Expandable intraluminal vascular graft
US5078736A (en) * 1990-05-04 1992-01-07 Interventional Thermodynamics, Inc. Method and apparatus for maintaining patency in the body passages
US5129883A (en) * 1990-07-26 1992-07-14 Michael Black Catheter
US5176664A (en) * 1990-10-09 1993-01-05 Kenneth Weisman Female voiding assist device and method
US5282824A (en) * 1990-10-09 1994-02-01 Cook, Incorporated Percutaneous stent assembly
US5217483A (en) * 1990-11-28 1993-06-08 Numed, Inc. Intravascular radially expandable stent
US5108420A (en) * 1991-02-01 1992-04-28 Temple University Aperture occlusion device
US5197978B1 (en) * 1991-04-26 1996-05-28 Advanced Coronary Tech Removable heat-recoverable tissue supporting device
US5197978A (en) * 1991-04-26 1993-03-30 Advanced Coronary Technology, Inc. Removable heat-recoverable tissue supporting device
US5304200A (en) * 1991-05-29 1994-04-19 Cordis Corporation Welded radially expandable endoprosthesis and the like
US5183085A (en) * 1991-09-27 1993-02-02 Hans Timmermans Method and apparatus for compressing a stent prior to insertion
US5314472A (en) * 1991-10-01 1994-05-24 Cook Incorporated Vascular stent
US5211658A (en) * 1991-11-05 1993-05-18 New England Deaconess Hospital Corporation Method and device for performing endovascular repair of aneurysms
US5383892A (en) * 1991-11-08 1995-01-24 Meadox France Stent for transluminal implantation
US6562063B1 (en) * 1993-10-22 2003-05-13 Scimed Life Systems, Inc. Stent delivery apparatus and method
US5916234A (en) * 1993-12-28 1999-06-29 Advanced Cardiovascular Systems, Inc. Expandable stents and method for making same
US5879370A (en) * 1994-02-25 1999-03-09 Fischell; Robert E. Stent having a multiplicity of undulating longitudinals
US5733303A (en) * 1994-03-17 1998-03-31 Medinol Ltd. Flexible expandable stent
US5609605A (en) * 1994-08-25 1997-03-11 Ethicon, Inc. Combination arterial stent
US5735871A (en) * 1994-12-09 1998-04-07 Sgro; Jean-Claude Self-expanding endoprosthesis
US6348065B1 (en) * 1995-03-01 2002-02-19 Scimed Life Systems, Inc. Longitudinally flexible expandable stent
US5601593A (en) * 1995-03-06 1997-02-11 Willy Rusch Ag Stent for placement in a body tube
US5755772A (en) * 1995-03-31 1998-05-26 Medtronic, Inc. Radially expansible vascular prosthesis having reversible and other locking structures
US6183508B1 (en) * 1996-02-08 2001-02-06 Schneider Inc Method for treating a vessel with a titanium alloy stent
US5888201A (en) * 1996-02-08 1999-03-30 Schneider (Usa) Inc Titanium alloy self-expanding stent
US5707387A (en) * 1996-03-25 1998-01-13 Wijay; Bandula Flexible stent
US5749825A (en) * 1996-09-18 1998-05-12 Isostent, Inc. Means method for treatment of stenosed arterial bifurcations
US6051021A (en) * 1997-05-27 2000-04-18 Medicorp, S.A. Self-expanding endoprosthesis
US5913895A (en) * 1997-06-02 1999-06-22 Isostent, Inc. Intravascular stent with enhanced rigidity strut members
US6251134B1 (en) * 1999-02-28 2001-06-26 Inflow Dynamics Inc. Stent with high longitudinal flexibility
US6517547B1 (en) * 1999-09-07 2003-02-11 Angiomed Gmbh & Co. Medizintechnik Kg Stent delivery system
US6245100B1 (en) * 2000-02-01 2001-06-12 Cordis Corporation Method for making a self-expanding stent-graft
US6562067B2 (en) * 2001-06-08 2003-05-13 Cordis Corporation Stent with interlocking elements
US20070150049A1 (en) * 2004-03-16 2007-06-28 Alveolus, Inc. Stent

Cited By (27)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US9445798B2 (en) 2004-03-19 2016-09-20 St. Jude Medical, Cardiology Division, Inc. Multi-layer braided structures for occluding vascular defects
US20080200945A1 (en) * 2004-03-19 2008-08-21 Aga Medical Corporation Device for occluding vascular defects
US20060241690A1 (en) * 2004-03-19 2006-10-26 Aga Medical Corporation Multi-layer braided structures for occluding vascular defects and for occluding fluid flow through portions of the vasculature of the body
US20090062841A1 (en) * 2004-03-19 2009-03-05 Aga Medical Corporation Device for occluding vascular defects
US9877710B2 (en) 2004-03-19 2018-01-30 St. Jude Medical, Cardiology Division, Inc. Multi-layer braided structures for occluding vascular defects and for occluding fluid flow through portions of the vasculature of the body
US8313505B2 (en) 2004-03-19 2012-11-20 Aga Medical Corporation Device for occluding vascular defects
US8398670B2 (en) 2004-03-19 2013-03-19 Aga Medical Corporation Multi-layer braided structures for occluding vascular defects and for occluding fluid flow through portions of the vasculature of the body
US20070265656A1 (en) * 2004-03-19 2007-11-15 Aga Medical Corporation Multi-layer braided structures for occluding vascular defects
US8777974B2 (en) 2004-03-19 2014-07-15 Aga Medical Corporation Multi-layer braided structures for occluding vascular defects
US9445799B2 (en) 2004-03-19 2016-09-20 St. Jude Medical, Cardiology Division, Inc. Multi-layer braided structures for occluding vascular defects
US11134933B2 (en) 2004-03-19 2021-10-05 St. Jude Medical, Cardiology Division, Inc. Multi-layer braided structures for occluding vascular defects
US9039724B2 (en) 2004-03-19 2015-05-26 Aga Medical Corporation Device for occluding vascular defects
US20090210048A1 (en) * 2008-02-18 2009-08-20 Aga Medical Corporation Stent/stent graft for reinforcement of vascular abnormalities and associated method
US8747453B2 (en) * 2008-02-18 2014-06-10 Aga Medical Corporation Stent/stent graft for reinforcement of vascular abnormalities and associated method
US11529249B2 (en) 2013-03-13 2022-12-20 DePuy Synthes Products, Inc. Braided stent with expansion ring and method of delivery
US9034028B2 (en) * 2013-03-13 2015-05-19 DePuy Synthes Products, Inc. Braid expansion ring with markers
US11452623B2 (en) 2013-03-13 2022-09-27 DePuy Synthes Products, Inc. Braided stent with expansion ring and method of delivery
US20140277376A1 (en) * 2013-03-13 2014-09-18 DePuy Synthes Products, LLC Braid expansion ring with markers
US10821010B2 (en) 2014-08-27 2020-11-03 DePuy Synthes Products, Inc. Method of making a multi-strand implant with enhanced radiopacity
US10821008B2 (en) 2016-08-25 2020-11-03 DePuy Synthes Products, Inc. Expansion ring for a braided stent
US11129738B2 (en) 2016-09-30 2021-09-28 DePuy Synthes Products, Inc. Self-expanding device delivery apparatus with dual function bump
US20180110636A1 (en) * 2016-10-21 2018-04-26 DePuy Synthes Products, Inc. Expansion ring for a braided stent
US10182927B2 (en) * 2016-10-21 2019-01-22 DePuy Synthes Products, Inc. Expansion ring for a braided stent
US11090175B2 (en) 2018-07-30 2021-08-17 DePuy Synthes Products, Inc. Systems and methods of manufacturing and using an expansion ring
US11497638B2 (en) 2018-07-30 2022-11-15 DePuy Synthes Products, Inc. Systems and methods of manufacturing and using an expansion ring
US11357648B2 (en) 2018-08-06 2022-06-14 DePuy Synthes Products, Inc. Systems and methods of using a braided implant
US11039944B2 (en) 2018-12-27 2021-06-22 DePuy Synthes Products, Inc. Braided stent system with one or more expansion rings

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JP4046760B2 (en) 2008-02-13
JP2005324053A (en) 2005-11-24
JPH10500595A (en) 1998-01-20
US6451052B1 (en) 2002-09-17
EP0759730B1 (en) 1999-02-10
DE69507800T2 (en) 1999-07-22
ATE176587T1 (en) 1999-02-15
US20030208263A1 (en) 2003-11-06
WO1995031945A1 (en) 1995-11-30
JP4351656B2 (en) 2009-10-28
EP0759730A1 (en) 1997-03-05
CA2190012C (en) 2005-09-20
JP2007236966A (en) 2007-09-20
US6582461B1 (en) 2003-06-24
US8221491B1 (en) 2012-07-17
CA2190012A1 (en) 1995-11-30
ES2126896T3 (en) 1999-04-01

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