US20030236568A1 - Multi-lobed frame based unidirectional flow prosthetic implant - Google Patents
Multi-lobed frame based unidirectional flow prosthetic implant Download PDFInfo
- Publication number
- US20030236568A1 US20030236568A1 US10/431,967 US43196703A US2003236568A1 US 20030236568 A1 US20030236568 A1 US 20030236568A1 US 43196703 A US43196703 A US 43196703A US 2003236568 A1 US2003236568 A1 US 2003236568A1
- Authority
- US
- United States
- Prior art keywords
- structural frame
- membrane
- valve
- distal
- distal crowns
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Abandoned
Links
Images
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS 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
- A61F2/00—Filters 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
- A61F2/02—Prostheses implantable into the body
- A61F2/24—Heart valves ; Vascular valves, e.g. venous valves; Heart implants, e.g. passive devices for improving the function of the native valve or the heart muscle; Transmyocardial revascularisation [TMR] devices; Valves implantable in the body
- A61F2/2412—Heart valves ; Vascular valves, e.g. venous valves; Heart implants, e.g. passive devices for improving the function of the native valve or the heart muscle; Transmyocardial revascularisation [TMR] devices; Valves implantable in the body with soft flexible valve members, e.g. tissue valves shaped like natural valves
- A61F2/2415—Manufacturing methods
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS 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
- A61F2/00—Filters 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
- A61F2/02—Prostheses implantable into the body
- A61F2/24—Heart valves ; Vascular valves, e.g. venous valves; Heart implants, e.g. passive devices for improving the function of the native valve or the heart muscle; Transmyocardial revascularisation [TMR] devices; Valves implantable in the body
- A61F2/2412—Heart valves ; Vascular valves, e.g. venous valves; Heart implants, e.g. passive devices for improving the function of the native valve or the heart muscle; Transmyocardial revascularisation [TMR] devices; Valves implantable in the body with soft flexible valve members, e.g. tissue valves shaped like natural valves
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS 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
- A61F2/00—Filters 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
- A61F2/02—Prostheses implantable into the body
- A61F2/24—Heart valves ; Vascular valves, e.g. venous valves; Heart implants, e.g. passive devices for improving the function of the native valve or the heart muscle; Transmyocardial revascularisation [TMR] devices; Valves implantable in the body
- A61F2/2412—Heart valves ; Vascular valves, e.g. venous valves; Heart implants, e.g. passive devices for improving the function of the native valve or the heart muscle; Transmyocardial revascularisation [TMR] devices; Valves implantable in the body with soft flexible valve members, e.g. tissue valves shaped like natural valves
- A61F2/2418—Scaffolds therefor, e.g. support stents
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS 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
- A61F2/00—Filters 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
- A61F2/02—Prostheses implantable into the body
- A61F2/24—Heart valves ; Vascular valves, e.g. venous valves; Heart implants, e.g. passive devices for improving the function of the native valve or the heart muscle; Transmyocardial revascularisation [TMR] devices; Valves implantable in the body
- A61F2/2475—Venous valves
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS 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
- A61F2/00—Filters 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
- A61F2/82—Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/86—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure
- A61F2/90—Stents 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
- A61F2/91—Stents 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
- A61F2/915—Stents 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
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS 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
- A61F2/00—Filters 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
- A61F2/82—Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2002/825—Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents having longitudinal struts
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS 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
- A61F2/00—Filters 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
- A61F2/82—Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/86—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure
- A61F2/90—Stents 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
- A61F2/91—Stents 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
- A61F2/915—Stents 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
- A61F2002/91533—Stents 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
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS 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
- A61F2/00—Filters 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
- A61F2/82—Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/86—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure
- A61F2/90—Stents 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
- A61F2/91—Stents 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
- A61F2/915—Stents 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
- A61F2002/9155—Adjacent bands being connected to each other
- A61F2002/91558—Adjacent bands being connected to each other connected peak to peak
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS 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
- A61F2/00—Filters 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
- A61F2/82—Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/86—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure
- A61F2/90—Stents 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
- A61F2/91—Stents 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
- A61F2/915—Stents 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
- A61F2002/9155—Adjacent bands being connected to each other
- A61F2002/91575—Adjacent bands being connected to each other connected peak to trough
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS 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
- A61F2/00—Filters 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
- A61F2/82—Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/86—Stents in a form characterised by the wire-like elements; Stents in the form characterised by a net-like or mesh-like structure
- A61F2/90—Stents 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
- A61F2/91—Stents 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
- A61F2/915—Stents 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
- A61F2002/9155—Adjacent bands being connected to each other
- A61F2002/91583—Adjacent bands being connected to each other by a bridge, whereby at least one of its ends is connected along the length of a strut between two consecutive apices within a band
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS 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
- A61F2220/00—Fixations or connections for prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2220/0025—Connections or couplings between prosthetic parts, e.g. between modular parts; Connecting elements
- A61F2220/005—Connections or couplings between prosthetic parts, e.g. between modular parts; Connecting elements using adhesives
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS 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
- A61F2220/00—Fixations or connections for prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2220/0025—Connections or couplings between prosthetic parts, e.g. between modular parts; Connecting elements
- A61F2220/0058—Connections or couplings between prosthetic parts, e.g. between modular parts; Connecting elements soldered or brazed or welded
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS 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
- A61F2230/00—Geometry of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2230/0002—Two-dimensional shapes, e.g. cross-sections
- A61F2230/0028—Shapes in the form of latin or greek characters
- A61F2230/0054—V-shaped
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS 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
- A61F2230/00—Geometry of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2230/0063—Three-dimensional shapes
- A61F2230/0073—Quadric-shaped
- A61F2230/0078—Quadric-shaped hyperboloidal
Definitions
- the present invention relates to a medical device, and more particularly to a multi-lobed frame based unidirectional flow prosthetic valve, and the method for fabricating such valve.
- the human body has numerous biological valves that control fluid flow through body lumens and vessels.
- the circulatory system has various heart valves that allow the heart to act as a pump by controlling the flow of blood through the heart chambers, veins, and aorta.
- the venous system has numerous venous valves that help control the flow of blood back to the heart, particularly from the lower extremities.
- Heart valves are subject to disorders, such as mitral stenosis, mitral regurgitation, aortic stenosis, aortic regurgitation, mitral valve prolapse and tricuspid stenosis. These disorder are potentially life threatening.
- incompetent or damaged venous valves usually leak, allowing the blood to improperly flow back down through veins away from the heart (regurgitation reflux or retrograde blood flow). Blood can then stagnate in sections of certain veins, and in particular, the veins in the lower extremities.
- Surgical procedures for incompetent or damaged venous valves include valvuloplasty, transplantation, and transposition of veins. However, these surgical procedures provide somewhat limited results. The leaflets of some venous valves are generally thin, and once the valve becomes incompetent or destroyed, any repair provides only marginal relief.
- the present invention relates to a medical device, and in particular, to a frame-based valve.
- One embodiment of the invention comprises a radially expandable structural frame having a plurality of distal crowns or lobes.
- the structural frame is formed from a lattice of interconnected elements, and has a substantially cylindrical configuration with first and second open ends and a longitudinal axis extending there between.
- a tubular biocompatible membrane is coaxially disposed over at least a portion of the structural frame such that the structural frame supports the biocompatible membrane assembly in a slack condition between the distal crowns.
- the prosthetic valve may further have a valve strut attached to at least one of the distal crowns that extends in a distal direction substantially parallel to the longitudinal axis.
- the biocompatible membrane assembly may also extend in a distal direction past the distal crowns.
- the prosthetic valve comprises a radially expandable structural frame having a plurality of articulating distal crowns.
- the structural frame is formed from a lattice of interconnected elements, and has a substantially cylindrical configuration with first and second open ends and a longitudinal axis extending there between.
- a tubular biocompatible membrane is coaxially disposed over at least a portion of the structural frame such that the structural frame supports the biocompatible membrane assembly in a slack condition between the distal crowns.
- the prosthetic valve comprises a substantially cylindrical structural frame that has a hoop structure with a plurality of distal crowns.
- a substantially cylindrical biocompatible membrane assembly is attached to the structural frame such that the structural frame supports the biocompatible membrane assembly in a slack condition between the distal crowns.
- a prosthetic valve has a radially expandable structural frame comprising a cylindrical hoop structure having a plurality of distal and proximal crowns, a proximal anchor, and one or more connecting members.
- the proximal anchor has a substantially cylindrical configuration and is formed from a lattice of interconnected elements.
- the one or more connecting members has a first and a second end, the first end of each connecting member is attached to the proximal anchor and the second end of each connecting member is attached to the hoop structure.
- a biocompatible membrane assembly is coaxially disposed over the structural frame and attached to the proximal anchor, such that the biocompatible membrane assembly extends distally along the one or more connecting members.
- FIG. 1 shows a perspective view of a prosthetic venous valve in the deployed state according to one embodiment of the present invention.
- FIG. 2A shows a perspective view of the prosthetic venous valve structural frame in the deployed state
- FIG. 2B shows a close-up perspective view of a loop having inner and outer radii according to one embodiment of the present invention.
- FIG. 3A shows a perspective view of a prosthetic valve having two hoop structures according to another embodiment of the present invention.
- FIG. 3B shows a perspective view of a structural frame having two hoop structures according to another embodiment of the present invention.
- FIG. 3C shows a perspective view of a structural frame having two hoop structures attached with bridge members.
- FIG. 3D shows a perspective view of a prosthetic venous valve having connecting members connected between the sinusoidal structure and proximal anchor according to one embodiment of the present invention.
- FIG. 3E shows a perspective view of the prosthetic venous valve structural frame having connecting members connected between the sinusoidal structure and proximal anchor in a peak-to-peak configuration according to one embodiment of the present invention.
- FIG. 4A is a perspective view illustrating one embodiment of the expanded (deployed) prosthetic venous valve assembly in the open position.
- FIG. 4B is a section view illustrating one embodiment of the expanded (deployed) prosthetic venous valve assembly in the open position.
- FIG. 5A is a perspective view illustrating one embodiment of the expanded (deployed) prosthetic venous valve assembly in the closed position.
- FIG. 5B is a section view illustrating one embodiment of the expanded (deployed) prosthetic venous valve assembly in the closed position.
- FIG. 6A is a perspective view of a prosthetic valve having flexible distal crowns capable of deflecting inward during retrograde blood flow.
- FIG. 6B is a perspective view of a prosthetic valve according to an embodiment of the present invention.
- FIG. 6C is a perspective view of a prosthetic valve having valve struts according to an embodiment of the present invention.
- FIG. 6D is a perspective view illustrating a membrane limiting means according to one embodiment of the present invention.
- FIG. 6E is a perspective view illustrating a membrane limiting means according to one embodiment of the present invention.
- FIG. 6F is a perspective view illustrating a membrane limiting means according to one embodiment of the present invention.
- FIG. 6G is a perspective view of a prosthetic valve having valve struts according to an embodiment of the present invention.
- FIG. 7 is a flow diagram illustrating the steps to electro-statically spin a tubular membrane on a structural frame according to one embodiment of the present invention.
- FIG. 8A is section view illustrating the expanded (deployed) prosthetic venous valve assembly in the open position after some post processing according to one embodiment of the present invention.
- FIG. 8B shows a close-up section view illustrating a portion of the valve assembly after some post processing according to one embodiment of the present invention.
- FIG. 9 is a flow diagram illustrating the steps to electro-statically spin a tubular membrane on a structural frame according to one embodiment of the present invention.
- FIG. 10 is a flow diagram illustrating the steps to place a tubular membrane over a structural frame according to one embodiment of the present invention.
- the stent-based valves of the present invention provide a method for overcoming the difficulties associated with the treatment of valve insufficiency.
- stent based venous valves are disclosed to illustrate one embodiment of the present invention, one of ordinary skill in the art would understand that the disclosed invention can be equally applied to other locations and lumens in the body, such as, for example, coronary, vascular, non-vascular and peripheral vessels, ducts, and the like, including but not limited to cardiac valves, venous valves, valves in the esophagus and at the stomach, valves in the ureter and/or the vesica, valves in the biliary passages, valves in the lymphatic system and valves in the intestines.
- the prosthetic valve is designed to be percutaneously delivered through a body lumen to a target site by a delivery catheter.
- the target site may be, for example, a location in the venous system adjacent to an insufficient venous valve.
- the prosthetic venous valve functions to assist or replace the incompetent or damaged natural valve by allowing normal blood flow (antegrade blood flow) and preventing or reducing backflow (retrograde blood flow).
- FIG. 1 A perspective view of a prosthetic venous valve in the expanded (deployed) state according to one embodiment of the present invention is shown in FIG. 1.
- the prosthetic venous valve 100 comprises a structural frame 101 and a biocompatible membrane assembly 102 .
- the membrane assembly 102 is comprised of a tubular membrane, valve flaps and valve cusps.
- the flaps and cusps may be independent components attached to the tubular membrane to form the membrane assembly 102 , but are preferably part of, and integrated into, the tubular membrane.
- the valve flaps and valve cusps are formed into the tubular membrane by processing techniques as will be discussed in greater detail below.
- FIG. 2A a perspective view of the structural frame 101 according to one embodiment of the present invention is shown in FIG. 2A.
- the structural frame 101 consists of a stent based sinusoidal structure, having a single hoop section 200 A with one or more proximal and distal crowns (lobes) 205 , 206 respectively.
- proximal and distal crowns (lobes) 205 , 206 respectively.
- at least three distal crowns 206 are utilized as illustrated.
- this configuration is not meant to limit the scope of the invention.
- Various other configurations having one or more distal crowns 206 may be used, and would be understood by one of skill in the art.
- proximal and distal are typically used to connote a direction or position relative to a human body.
- the proximal end of a bone may be used to reference the end of the bone that is closer to the center of the body.
- distal can be used to refer to the end of the bone farthest from the body.
- proximal and distal are sometimes used to refer to the flow of blood to the heart, or away from the heart, respectively. Since the prosthetic valves described in this invention can be used in many different body lumens, including both the arterial and venous system, the use of the terms proximal and distal in this application are used to describe relative position in relation to the direction of fluid flow.
- proximal crown in the present application describes the upstream crown of structural frame 101 regardless of its orientation relative to the body.
- distal crown is used to describe the down stream crown on structural frame 101 regardless of its orientation relative to the body.
- proximal and distal to connote a direction describe upstream (retrograde) or downstream (antegrade) respectively.
- the structural frame is a stent-based structure. This configuration facilitates the percutaneous delivery of the prosthetic venous valve 100 through the vascular system in a compressed state. Once properly located, the stent-based venous valve 100 may be deployed to the expanded state.
- FIG. 2A The sinusoidal stent based structural frame illustrated in FIG. 2A is shown having an S shaped pattern. This configuration is shown for the purpose of example, and is not meant to be construed as limiting the scope of the invention. One of ordinary skill in the art would understand that other stent geometries having similar crowns may be used.
- the sinusoidal stent based structural frame 101 comprises a tubular configuration of structural elements having proximal and distal open ends and defining a longitudinal axis 106 extending there between.
- the structural frame 101 has a first diameter (not shown) for insertion into a patient and navigation through the vessels, and a second diameter D 2 for deployment into the target area of a vessel, with the second diameter being greater than the first diameter.
- the structural frame 101 and thus the stent based venous valve 100 , may be either a mechanical (balloon) or self-expanding stent based structure.
- the structural frame 101 comprises at least one hoop structure 200 A extending between the proximal and distal ends.
- the hoop structure 200 A includes a plurality of longitudinally arranged strut members 208 and a plurality of loop members 210 connecting adjacent struts 208 . Together, these strut members 208 and loop members 210 form the proximal and distal crowns 205 , 206 respectively. Adjacent struts 208 are connected at opposite ends in a substantially S or Z shaped pattern so as to form a plurality of cells. As previously discussed, one of ordinary skill in the art would recognize that the pattern shaped by the struts is not a limiting factor, and other shaped patterns may be used.
- the plurality of loops 210 have a substantially semi-circular configuration, having an inner radii 212 and outer radii 214 , and are substantially symmetric about their centers.
- the inner and outer radii 212 , 214 respectively, are shown in a close-up perspective view illustrated in FIG. 2B.
- FIGS. 1 and 2 show a structural frame 101 having a single hoop structure 200 A.
- this configuration is not meant to be construed as a limiting feature, and other configurations having a plurality of hoop structures are also contemplated by the present invention.
- FIGS. 3A through 3C illustrate a structural frame 101 having two hoop structures 200 A and 200 B according to another embodiment of the present invention.
- FIG. 3A shows a complete prosthetic valve 300 in the expanded (deployed) position, illustrating both the structural frame 101 and membrane assembly 102 .
- FIG. 3B is an illustration of just the structural frame 101 without the membrane assembly 102 .
- the hoop structures 200 A and 200 B are rigidly attached at complimentary points along their respective outer radii of the loops 210 .
- the hoop structures 200 A, 200 B may be attached with one or more bridge members 305 .
- Each bridge member 305 comprises two ends 316 A, 316 B.
- One end 316 A, 316 B of each bridge 305 is attached to one loop on one hoop.
- each bridge member 305 is connected at end 316 A to loop 210 on hoop section 200 A at a point 320 .
- the opposite end 316 B of each bridge member 314 is connected to loop 210 on hoop sections 200 B at a point 321 .
- connections between the hoop structures 200 A, 200 B etc. may be made at every loop member 210 around the circumference of the structure; or alternatively, at a subset of the loop members 210 around the circumference of the structure. In other words, connected loop members 210 alternate with unconnected loop members in some defined pattern.
- the anchor may be in the form of another sinusoidal stent based structure, such as the structures depicted in FIGS. 1 through 3C.
- any radially expandable structural frame that can aid in anchoring prosthetic valve is contemplated by the present invention.
- These anchors may be located downstream (proximal) or upstream (distal) from the lobed valve.
- FIG. 3D illustrates a prosthetic lobed valve 300 incorporating a proximal anchor and connecting members according to one embodiment of the invention.
- FIG. 3E shows the valve 300 structural frame 101 with the membrane structure 102 removed.
- the illustrated valve 300 comprises a single hoop structure 200 A having proximal and distal crowns 205 , 206 respectively.
- the structural frame also has an anchor 315 proximal to the hoop structure 200 A.
- the anchor 315 illustrated in FIGS. 3D and 3E is structurally similar to the sinusoidal stent based structure comprising the hoop structure 200 A.
- the anchor 315 comprises a tubular configuration of structural elements having proximal and distal open ends and defining a longitudinal axis 306 extending there between.
- the stent anchor 315 has a first diameter (not shown) for insertion into a patient and navigation through the vessels, and a second diameter D 2 for deployment into the target area of a vessel, with the second diameter being greater than the first diameter.
- the stent anchor 315 and thus the stent based venous valve 300 , may be either a mechanical (balloon) or self-expanding stent based structure.
- the stent anchor 315 comprises at least one hoop structure 336 extending between the proximal and distal ends.
- the hoop structure 336 includes a plurality of longitudinally arranged strut members 338 and a plurality of loop members 340 connecting adjacent struts 338 . As shown, the stent anchor 315 has three hoop structures.
- Adjacent struts 338 are connected at opposite ends in a substantially S or Z shaped pattern so as to form a plurality of cells.
- the plurality of loops 340 have a substantially semi-circular configuration, having an inner radii and outer radii, and are substantially symmetric about their centers.
- the connecting member 310 may be connected to the hoop structure 200 A (on the sinusoidal valve structure) and the proximal anchor 315 at various points along the structures. As illustrated in FIG. 3E, the connecting members 310 are connected between the proximal end of the hoop structure 200 A and the distal end of the proximal anchor 315 at the inflection point of the loop members. This configuration creates a “Peak-to-Peak” connection bridging the outer radii of the inflection point of loop members 210 on the hoop structure 200 A with the outer radii of the inflection point of the loop member 340 on the proximal anchor 315 .
- the connecting members 310 are connected to the inflection point of loop members 210 , 340 oriented directly opposite one another, and are evenly spaced along the circumference of the tubular structures. This configuration facilitates the radial expansion of the prosthetic valve from the collapsed (delivered) state to the expanded (deployed) state, and provides a substantially symmetrical valve configuration.
- the connecting members 310 may be connected between the hoop structure 200 A and proximal anchor 315 to create a “Peak-to-Valley” connection between the loop members 210 , 340 respectively (not shown).
- the connecting members 310 are connected to the proximal end of the hoop structure 200 A at the outer radii of the inflection point of loop member 210 , and the inner radii of the inflection point of loop member 340 on the proximal end of the proximal anchor 315 .
- the connecting members 310 may be connected between the distal end of the hoop structure 200 A and the proximal end of the proximal anchor 315 at the inflection point of the loop members 210 , 340 .
- This configuration creates a “Valley-to-Valley” connection bridging the inner radii of the inflection point of loop members 340 on the proximal anchor 315 with the inner radii of the inflection point of the loop member 210 on the hoop structure 200 A.
- the connecting members 310 may be connected between the strut members 208 of the hoop structure 200 A and the strut members 338 of the proximal anchor 315 .
- connections between the connecting members 310 and the hoops 200 may be made at every inflection point around the circumference of the structure; or alternatively, at a subset of the inflection points around the circumference of the structure. In other words, connected inflection points alternate with unconnected inflection points in some defined pattern.
- the connecting members 310 are attached between the sinusoidal stent based structure (having loop 200 A in FIGS. 3D and 3E) and the proximal anchor 315 to further support the biocompatible membrane assembly 102 (not shown in FIG. 3E).
- the connecting members 315 are substantially straight members, connecting the hoop structure 200 A and proximal anchor 315 in a direction substantially parallel to the longitudinal axis 306 .
- three connecting members 315 are shown in the illustrated embodiment, one of skill in the art would understand that one or more connecting members may be used.
- the connecting members 315 may be twisted in a helical fashion as they extend from the hoop structure 200 A to the proximal anchor 315 (not shown).
- the connection points between the connecting members 315 and the hoop structure 200 A, and the connecting members 105 and the proximal anchor 315 are rotationally phased 180 degrees from each other to provide the helical design.
- Each connecting member 310 may also be biased inward slightly toward the longitudinal centerline 306 , creating a structural frame 101 having an hour-glass shape with the minimum radius located substantially at the longitudinal midpoint along the connecting member 310 length (not shown).
- the proximal crowns 205 may similarly be biased inward. This configuration may assist the prosthetic valve 300 when closing by forming larger valve cusps.
- the materials for the structural frame 101 should exhibit excellent corrosion resistance and biocompatibility.
- the material comprising the structural frame 101 should be sufficiently radiopaque and create minimal artifacts during MRI.
- the present invention contemplates deployment of the prosthetic venous valve 100 by both assisted (mechanical) expansion, i.e. balloon expansion, and self-expansion means.
- the structural frames 101 is made from materials that can be plastically deformed through the expansion of a mechanical assist device, such as by the inflation of a catheter based balloon.
- a mechanical assist device such as by the inflation of a catheter based balloon.
- the frame 101 remains substantially in the expanded shape. Accordingly, the ideal material has a low yield stress (to make the frame 101 deformable at manageable balloon pressures), high elastic modulus (for minimal recoil), and is work hardened through expansion for high strength.
- the most widely used material for balloon expandable structures 101 is stainless steel, particularly 316 L stainless steel. This material is particularly corrosion resistant with a low carbon content and additions of molybdenum and niobium. Fully annealed, stainless steel is easily deformable.
- Alternative materials for mechanically expandable structural frames 101 that maintain similar characteristics to stainless steel include tantalum, platinum alloys, niobium alloys, and cobalt alloys.
- other materials, such as polymers and bioabsorbable polymers may be used for the structural frames 101 .
- the materials comprising the structural frame 101 should exhibit large elastic strains.
- a suitable material possessing this characteristic is Nitinol, a Nickel-Titanium alloy that can recover elastic deformations of up to 10 percent. This unusually large elastic range is commonly known as superelasticity.
- the structural frame 101 may be fabricated using several different methods. Typically, the structural frame 101 is constructed from sheet, wire (round or flat) or tubing, but the method of fabrication generally depends on the raw material form used.
- the structural frame 101 can be formed from wire using convention wire forming techniques, such as coiling, braiding, or knitting. By welding the wire at specific locations a closed-cell structure may be created. This allows for continuous production, i.e. the components of the structural frame 101 may be cut to length from a long wire mesh tube.
- convention wire forming techniques such as coiling, braiding, or knitting.
- the complete frame structure may be cut from a solid tube or sheet of material, and thus the structural frame 101 would be considered a monolithic unit.
- Laser cutting, water-jet cutting and photochemical etching are all methods that can be employed to form the structural frame 101 from sheet and tube stock.
- the structural frame 101 is radially expandable and assists in securing the prosthetic valve 100 to the inside wall of a body vessel such as a vein. Once deployed in the desired location, radially expandable structural frame (and thus the prosthetic valve 100 ) will expand to an outside diameter slightly larger that the inside diameter of the native vessel (not shown) and remain substantially rigid in place, anchoring the valve assembly to the vessel.
- the membrane assembly is formed from a flexible membrane-like biocompatible material that is affixed to the frame structure 101 .
- the membrane must be strong enough to resist tearing under normal use, yet thin enough to provide the necessary flexibility that allows the biocompatible membrane assembly 102 to open and close satisfactorily.
- FIGS. 4A and 4B are perspective and section views, respectively, illustrating one embodiment of the expanded (deployed) prosthetic venous valve assembly 100 in the open position.
- the membrane material may be a biological material, such as a vein or small intestine submucosa (SIS), but is preferably a synthetic material such as a polymer, for example an elastic or elastomeric polymer, including a fluoropolymer, fluoroelastomer, or a bioabsorbable material, such as a bioabsorbable polymer or bioabsorbable elastomer.
- Bioabsorbable materials may allow cells to grow and form a tissue membrane (or valve flaps) over the bioabsorbable membrane. The bioabsorbable membrane then absorbs into the body, leaving the tissue membrane and/or flaps in place to act as a new natural tissue valve.
- the synthetic material may be reinforced with a fiber, such as an electro-statically spun (ESS) fiber, porous foam, such as ePTFE, or mesh.
- ESS electro-statically spun
- the flexible membrane like biocompatible material is formed into a tube (membrane tubular structure 400 ) placed over and around the structural frame 101 .
- the membrane tubular structure 400 has a first (distal) and second (proximal) ends 401 , 402 respectively, and preferably also has integrated valve flaps 403 and valve cusps 404 . These components together comprise the membrane assembly 102 .
- the first end 401 of the membrane tubular structure 400 is located at and between the distal crowns 206 .
- the second end 402 of the membrane tubular structure 400 is preferably located proximal to at least one half of the most proximal hoop structure, e.g. 200 B in FIG. 3B.
- the membrane structure 400 completely covers the proximal most hoop structure to the proximal crowns 205 . This configuration allows the structural frame 101 to expand the membrane tubular structure 400 into the native vessel wall, anchoring the membrane tubular structure 400 in place, and providing adequate sealing against retrograde blood flow.
- the distal end 401 of the membrane tubular structure 400 terminates with the valve flaps 403 .
- the number of valve flaps 403 is directly proportional to the number of distal crowns 206 supporting the membrane tubular assembly 102 .
- the design of the valve flaps 403 , and for that matter valve cusps 404 are such that the tubular membrane structure 400 between the distal crowns in not tightly drawn or taut. This “slack” facilitates closing the valve by allowing the valve cusps 404 to act as pockets that fill during retrograde flow. Conversely, during antegrade flow, the additional slack in the tubular membrane structure 400 is pushed to the vessel wall, allowing blood to flow through the valve leaflets.
- valve flaps 403 are sufficiently pliable and supple to easily open and close as the blood flow changes from antegrade to retrograde. When the valve flaps 403 close (during retrograde flow) the interior surfaces of the flaps 403 and/or membrane tubular structure 400 come into contact to prevent or adequately reduce retrograde blood flow.
- valve cusps 404 are formed into the membrane tubular structure 400 .
- the valve cusps 404 are defined generally by the intersection of the distal crowns 206 and membrane tubular structure 400 , and are preferably formed at least in part by the slack tubular membrane 400 between the distal crowns 206 .
- cusps are not meant to limit the scope of this invention.
- the term “cusps” is often more aptly used to describe the valve members in semilunar valves, such as the aortic and pulmonary valves, this discussion refers to both the cusps of semilunar valves and the “leaflets” of venous and atrioventricular valves. Accordingly, it should be understood that the aspects discussed in relation to these valves could be applied to any type of mammalian valve, including heart valves, venous valves, peripheral valves, etc.
- FIGS. 5A and 5B show perspective and section views, respectively, illustrating one embodiment of the expanded (deployed) prosthetic venous valve assembly 100 in the closed position.
- the distal crowns 206 are flexible and capable of deflecting inward during retrograde blood flow, further assisting valve 100 when closing and opening.
- a perspective view illustrating an example of this embodiment is shown in FIG. 6A.
- flexible distal crown 606 articulate inward in direction 608 to assist closing the valve 100 .
- the flexible distal crowns 606 may pivot along a pivot line 610 as shown, or gradually bend inward along their length.
- the membrane assembly 102 is normally configured in the open position, and only moves to the closed position upon retrograde blood flow. This configuration minimizes interference with blood flow (minimized blocking) and reduces turbulence at and through the valve.
- the flexible distal crowns 606 in this embodiment have an inferior radial stiffness, and provide a natural bias against the movement of the membrane assembly 102 to the closed position. This bias assists the valve flaps 403 and valve cusps 404 when returning to the open position.
- the bias towards opening the membrane assembly 102 (against closing) be sufficiently high to commence opening the valve before antegrade blood flow begins, i.e. during a point in time when the blood flow is stagnant (there is neither antegrade nor retrograde blood flow), or when minimal retrograde flow is experienced.
- valve assembly normally configured in the closed position, biased closed, and only open upon antegrade flow.
- valve membrane assembly 102 may extend past the distal end of the structural frame 101 , i.e. past distal crowns 206 , in a distal direction as shown in FIG. 6B.
- the extended section 602 of valve membrane 102 will collapse upon itself, thus limiting or preventing fluid flow back through the valve.
- the valve membrane 102 distal the structural frame 101 i.e. membrane section 602
- the membrane assembly 102 may have ribs or thickened sections processed into the membrane to provide sufficient rigidity.
- one or more valve struts may extend distally from the end of the structural frame 101 providing rigidity sufficient to support the valve membrane 102 , particularly membrane section 602 from inverting. These valve struts may be an integral part of the structural frame 101 , and made from similar material.
- FIG. 6C illustrates a valve 100 having valve struts 630 according to one embodiment of the present invention.
- the valve struts 630 extend from the distal end of the structural frame 101 , in particular, from the outside radii 214 of the distal crown 206 comprising the hoop structure 200 A.
- the valve strut 630 may extend from the inside radii 212 of the proximal crown 205 comprising the hoop structure 200 A. This alternate embodiment is shown in FIG. 6G. Still other embodiments having different connection points would be understood by one of skill in the art.
- valve struts 630 are shown for illustrative purposes, this exemplary embodiment is not meant to limit the scope of the invention.
- One of skill in the art would understand that one or more valve struts may be used and still accomplish the general intent of the invention.
- the membrane assembly 102 is made from a flexible membrane-like biocompatible material formed into the membrane tubular structure 400 .
- the membrane 400 can be woven, non-woven (such as electrostatic spinning), mesh, knitted, film or porous film (such as foam).
- the membrane assembly 102 may be fixedly attached to the structural frame by many different methods, including attachment resulting from radial pressure of the structural frame 101 against the membrane assembly 102 , attachment by means of a binder, heat, or chemical bond, and/or attachment by mechanical means, such as welding, suturing or coating.
- some of the membrane assembly 102 such as distal end 402 of tubular membrane 400 , is slideably attached to the structural frame 101 , particularly along valve struts 630 . Allowing the distal end 401 to slide along the valve struts 630 may allow or improve the opening and closing of the flaps 403 . The sliding movement may also assist the cusps 404 when filling and emptying.
- a limiting device may be integrated into the prosthetic valve 100 to limit the sliding movement of the membrane assembly 102 .
- Examples of limiting devices are shown in FIGS. 6D to 6 F.
- a stop 600 (illustrated as stop 600 A, 600 B, and 600 C in FIGS. 6D to 6 F respectively) is integrated into the valve struts 630 .
- the membrane assembly 102 is wrapped around the valve struts 630 and bonded to itself to form a loop collar 605 .
- the loop collar 605 must be sized to inhibit the distal end 402 of the membrane assembly 102 from sliding past the stop 600 .
- valve struts 630 has a thickened or “bulbous” section forming stop 600 A.
- FIG. 6E illustrates an undulating stop 600 B configuration.
- FIG. 6F shows the stop 600 C configured as a double bulbous section. It should be noted that the various configurations illustrated in FIGS. 6D through 6F are exemplary. One of ordinary skill in the art would understand that other configurations of stops may used.
- the tubular membrane 400 is manufactured from a fiber reinforced elastomer, such as an elastomeric fluoropolymer.
- the elastomer allows the tubular membrane 400 to be extremely thin and elastic, while the fiber provides the necessary strength.
- One method used to produce this type of reinforced membrane valve is an Electro-Static Spinning (ESS) process.
- ESS Electro-Static Spinning
- a reinforcing fiber may be would around the structural frame 101 , and an ESS membrane formed over the reinforcing fiber and structural frame 101 .
- the ESS process can be used to form a tubular membrane on many different types of structural frames, including frames associated with stents, stent grafts, valves, including percutaneously delivered venous valve, AAA (Abdominal Aortic Aneurysm) devices, local drug delivery devices, and the like.
- the disclosure of the ESS process for forming the tubular membrane 400 on the structural frame of a stent-based venous valve is exemplary, and thus not meant to limit the scope of this invention.
- FIG. 7 shows the steps for electro-statically spinning a reinforced tubular membrane onto a structural frame according to one embodiment of the present invention.
- the ESS process comprises first placing a transfer sheath over a spinning mandrel as shown in step 700 .
- the transfer sheath is a thin material that is used to prevent the ESS spun fiber from adhering to the mandrel. In instances where the mandrel itself is not electrically conducting, the transfer sheet may also provide the necessary electrical conductivity to attract the ESS spun fiber.
- the transfer sheath comprises a thin polymer tube, preferably fluoropolymer, of such a thickness that it can be easily deformed, and preferably collapsed, so that it is capable of being withdrawn conveniently from the lumen of the structural frame 101 and/or membrane tubular structure 400 .
- a transfer sheath made of other fibrous or sheet materials, such as other polymer, polymeric or metallic materials is not excluded. Most preferably, the transfer sheath will be made of an ePTFE tube.
- the ePTFE tube may be first coated with gold on at least a portion of the interior surface before placing the tube on the mandrel. This process may be completed by coating the inside of the tube, but is preferably done by coating the exterior of the ePTFE tube and then inverting the tube so that the gold coating is on the interior surface. The process may also be completed by inverting the tube so that the interior surface to be coated is exposed on exterior of the tube, coating the now exposed interior surface, and the inverting the tube so that the interior coated surface is back on the inside of the tube.
- the spinning mandrel is electrically conducting, and more preferably, is a metal coated with Teflon®.
- electrical conduction may not be essential.
- the spinning mandrel may be of any suitable material, including plastic material. Non-conductors may be used so long as the charge is capable of being transferred (i.e. bleed off) onto the transfer sheet or through the material itself.
- the spinning mandrel may be hollow or solid, and preferably has a smooth surface to facilitate sliding between the transfer sheath and mandrel during removal. However, it may be desirable to maintain some degree of frictional resistance between the transfer sheath and mandrel to reduce slippage between the two components during the ESS process.
- valve structural frame 101 is then placed on the transfer sheath, step 710 , and the ESS fiber is spun directly onto the valve structural frame 101 as shown in step 720 .
- the structural frame 101 is configured in the expanded or deployed state prior to placing the structural frame 101 on the spinning mandrel. This is generally the case when the structural frame 101 is of the self-expanding design. In other embodiments, such as balloon-expandable designs, the expansion mechanism may be integrated within the spinning mandrel to expand the structural frame during the spinning process.
- the expandable mandrel may also be used for electro-statically spinning a fiber onto a self-expanding structural frame 101 .
- the self-expanding structural frame 101 is placed on the spinning mandrel in the expanded state, and the expansion mechanism on the expandable mandrel is mandrel activated to further radially expand the structural frame to a “super-expanded” state.
- ESS fiber is then spun directly onto the super-expanded structural frame 101 .
- the larger diameter of the super-expanded structural frame 101 allows more material to be deposited on the structural frame, creating slack between the distal crowns, which may result in less post processing procedures. Post processing is described in step 760 .
- Electro-static spinning of a fiber is generally known in the art, and typically involves creating an electrical potential between a source component, i.e. the fiber or preferably a fiber forming liquid, and a downstream component, i.e. the spinning mandrel, transfer sheath or structural frame.
- the electrical potential causes the source component, typically the fiber forming liquid, to be attracted to, and thus move towards, the downstream component.
- the electrical potential is created by providing an electrical charge to either the source or downstream component, and grounding the other component.
- the source component will receive an electrical charge, while the downstream component is grounded.
- a fiber forming liquid is introduced into an electric field, whereby the fiber forming liquid is caused to produce a charged fiber.
- a device introduction device introducing the fiber forming liquid into the process is electrically charged, thus causing the fiber forming liquid to assume a like charge.
- the fiber forming liquid may be introduced into the process, including spraying the fiber forming liquid from a nozzle, or injecting the fiber forming liquid from a needle, orifice or drip tube.
- the fiber forming liquid is sufficiently viscous to be extruded into the process with an extrusion device.
- the fiber forming liquid is introduced into the process, it is hardened to form the ESS fiber.
- Hardening of the liquid into an ESS fiber may be accomplished, for example, by cooling the liquid until the fiber forming liquid will not lose its fibrous shape.
- Other methods for hardening the fiber may also include hardening by introducing a chemical hardener into the fiber forming liquid, or directing an air stream over the electrically drawn fiber forming liquid stream.
- a polymer is put into solution with a solvent to form a viscous fiber forming liquid. As the fiber forming liquid is drawn from the introducer device, the solvent comes out of solution forming the polymer fiber.
- Drying techniques may include, for example, applying heat or airflow to or over the coated fiber spun frame assembly.
- the solvent may dry naturally without applying artificial drying techniques.
- the viscosity of the fiber forming liquid may be adjusted based on the material used for the source component, and the percent solids desired as the source component reaches the downstream component. Typical concentrations range from 2 to 100 percent. The choice of concentration depends on the material, its molecular weight, the solvent efficiency, and temperature. The concentration and temperature also control the diameter of the fiber. These viscosities will typically produce a fiber at the downstream component having percent solids in the range of about 95 percent to about 100 percent, and preferably over 99 percent. This is desirable in order to produce structures that contain entangled or point bonded fibers. Concentrations lower than 95 percent can be used if it is desired to allow filaments to fuse together into a sheet-like barrier structure.
- the hardened fiber is then collected onto the structural frame. Collecting of the fiber involves attracting the ESS fiber to the downstream component (i.e. spinning mandrel, transfer sheath or structural frame) of the ESS system, while spinning the downstream component.
- a downstream component is grounded to complete the electric potential between the source and downstream component, and thus attract the ESS fiber.
- a downstream component may be electrically charged to attract the ESS fiber where the source component is grounded.
- various combinations of downstream components may be electrically charged to enhance electrical conductivity and reduce the time it takes to build up the ESS layer.
- Particular ESS fibers suitable for this spinning process include fluoropolymers, such as a crystalline fluoropolymer with an 85/15% (weight/weight ratio) of vinylidene fluoride/hexafluoropropylene (VDF/HFP).
- fluoropolymers such as a crystalline fluoropolymer with an 85/15% (weight/weight ratio) of vinylidene fluoride/hexafluoropropylene (VDF/HFP).
- Solvay Solef® 21508 and Kynarflex 2750-01 are two such examples.
- bioabsorbable polymers such as polyglycolic acid, polylactic acid, poly (paradioxanone), polycaprolactone, poly (trimethylenecarbonate) and their copolymers
- semicrystalline bioelastomers such as 60/40% (weight/weight ratio) of polylactic acid/polycaprolactone (PLA/PCL), 65/35 (weight/weight ratio) of polyglycolic acid/polycaprolactone (PGA/PCL), or nonabsorbable siliconized polyurethane, non-siliconized polyurethanes, siliconized polyureaurethane, including siliconized polyureaurethane end capped with silicone or fluorine end groups, or natural polymers in combination thereof.
- PLA/PCL polylactic acid/polycaprolactone
- PGA/PCL polyglycolic acid/polycaprolactone
- nonabsorbable siliconized polyurethane non-siliconized polyurethanes
- siliconized polyureaurethane including siliconized polyurea
- the spinning process should be continued until an ESS fiber tube, or fabric, is formed having a wall thickness of between 5 ⁇ m and 100 ⁇ m or more, preferably, approximately 20 ⁇ m.
- the ESS fiber spun structural frame 101 is then removed from the spinning mandrel, step 730 , before the transfer sheath is removed from the fiber spun frame, step 740 .
- the fiber spun structural frame is coated in a solution of polymer, such as fluoroelastomer, as shown in step 750 .
- the fiber spun structural frame is first dip coated in a polymer solution, and then spun about its longitudinal axis to more evenly distribute the coating.
- the fiber spun structural frame is not first removed from the spinning mandrel. Instead, the frame/mandrel assembly is dip coated and spun before removing the fiber spun structural frame from the spinning mandrel. Still other methods for coating the fiber spun structural frame would be obvious to one of skill in the art.
- the coating process may act to encapsulate and attach at least a portion of the spun ESS reinforcement fiber to the structural frame 101 . It should be noted that it in some embodiments of the invention, some movement between the membrane assembly 102 and the structural frame 101 is desired. Accordingly, not all of the ESS fiber spun structural frame may be coated.
- the coating process may also remove some porosity of the membrane material. However, it may be desirable to maintain some porosity in particular embodiments to promote biological cell grown on and within the membrane tubular structure.
- the coating solution preferably comprises a polymer put into solution with a solvent. As the solvent evaporates, the polymer comes out of solution forming the coating layer. Accordingly, for the process to work properly, the solvent used in the coating solution should not dissolve or alter the ESS fibers being coated.
- a coating solution of 60/40% VDF/HFP in methanol has been found to be a suitable solution for coating an ESS fiber comprised of 85/15% VDF/HFP.
- the polymer comprising the coating is Daikin's Dai-El G701BP, which is a 60/40% VDF/HFP.
- Daikin's Dai-El T630 a thermoplastic elastomer based on vinylidene fluoride/hexafluoropropylene/tetrafluoroethylene (VDF/HFP/TFE) can also be used.
- VDF/HFP/TFE vinylidene fluoride/hexafluoropropylene/tetrafluoroethylene
- other materials having suitable characteristics may be used for the coating, for example, other polymers, such as siliconized polyurethane, including Polymer Technology Group's Pursil, Carbosil, Purspan and Purspan F.
- the coating process may be repeated until the desired characteristics and thickness are achieved.
- a thickness of between 12 ⁇ m and 100 ⁇ m and preferably between 25 ⁇ m and 50 ⁇ m has been found to be acceptable.
- the post processing step 760 may be used to form or shape, for example, a valve cusp, similar to cusp 404 , in the membrane tubular structure 400 .
- post processing may change the characteristics of the membrane tubular structure 400 by thickening or thinning the membrane in particular locations. Thickening the membrane may add rigidity and reinforcement to a particular area. Thinning the membrane may make the membrane more pliable, which is a desirable characteristic for the valve flaps 403 .
- Still other post processing procedures may change the physical shape of the membrane tubular structure 400 , for example, by forming the loop collar 605 along the distal edge of membrane tubular structure 400 .
- the loop collar 605 may assist in controlling the movement (translational and circumferential) of the membrane assembly 102 along the valve struts 630 .
- the loop collars 605 may also reduce fatigue and tear stresses in the membrane.
- FIGS. 8A and 8B show an example of the result of a post processing step that forms a loop collar 605 according to one embodiment of the present invention.
- the membrane tubular structure 400 is wrapped around at least one element of structural frame 101 (valve struts 630 ) and bonded to itself at bond point 800 .
- FIG. 9 Another method for electro-statically spinning a tubular membrane onto a radially expandable structural frame according to another embodiment of the present invention is shown in FIG. 9.
- this alternative method provides an ESS spun membrane on the inside, as well as the outside of the structural frame.
- the inner and outer ESS spun membranes may mechanically adhere to each other, and in a sense encapsulated the structural frame.
- This configuration provides some additional features, including having a smoother interior surface that reduces turbulence, improves flow dynamics and lowers the chance of thrombosis formation.
- the ESS process comprises first placing a transfer sheath over a spinning mandrel as shown in step 900 . It should be noted that under certain circumstances it may not be necessary to use the transfer sheath. Such circumstances may include, for example, where the spinning mandrel is electro-statically conducting and has a surface or surface treatment that will prevent the ESS spun fiber from adhering to the mandrel.
- An ESS fiber is then spun directly onto the transfer sheath creating an inner coat membrane as shown in step 910 .
- the ESS process should continue until an ESS tube is formed having a wall thickness of between 2 ⁇ m and 50 ⁇ m or more, and preferably, approximately 20 ⁇ m.
- the inner coat membrane covers some or all of the interior surface of structural frame 101 .
- the structural frame 101 is then radially expanded and placed over the inner coat membrane on the spinning mandrel as shown in step 920 . Expansion of the structural frame 101 may be achieved by several different methods. One method includes taking advantage of the thermal and shape memory characteristics of particular materials.
- shape memory materials such as Nitinol
- Cooling the Nitinol structural frame 101 before expansion allows the structural frame to remain in the expanded configuration until being heated. Accordingly, the Nitinol structural frame 101 can be cooled, expanded, and then placed over the inner coat membrane. Once in place, the structural frame can be heated to activate the Nitinol memory characteristics, causing the Nitinol structural frame 101 to contract to the pre-expansion size and configuration.
- the structural frame 101 is sized such that when configured in the expanded or deployed state, it will fit tightly over the inner coat membrane on the spinning mandrel.
- the structural frame 101 may have to be radially expanded (“super-expanded”) to a diameter slightly larger than the expanded deployed state to allow the structural frame 101 to fit over the inner coat membrane.
- step 930 Once the structural frame 101 is placed over the inner coat membrane, another ESS fiber is spun directly onto the structural frame, as shown in step 930 , to form a top-coat membrane.
- the ESS process should continue until the top-coat membrane tube is formed having a wall thickness of between 2 ⁇ m and 50 ⁇ m or more, and preferably, approximately 20 ⁇ m.
- the top-coat membrane may cover and adhere to the inner coat membrane through the interstitial spaces between the elements that comprise the structural frame 101 .
- the structural frame 101 is configured on the mandrel in the expanded deployed state prior to spinning the top-coat membrane. In other embodiments, it may be desirable to expand (super expand) the structural frame 101 on the spinning mandrel during or prior to the spinning process. This procedure may alter the configuration and properties of the spun membrane, resulting in less post processing of the membrane. Post processing is described in step 960 .
- the structural frame 101 with the inner coat and top coat membranes, is then removed from the spinning mandrel, as shown in step 940 , and coated with a solution of highly elastic polymer as shown in step 950 .
- the coating process may be achieved using several different coating methods, including spin coating, spray coating, dip coating, chemical vapor deposition, plasma coating, co-extrusion coating and insert molding.
- a representative elastomeric polymer is a fluoroelastomer.
- the coating process may be repeated until the desired characteristics and thickness are achieved.
- FIG. 10 Another, more preferred method for forming the membrane material over and around the structural frame 101 is shown in FIG. 10. As described earlier, this method is presented in the context of a prosthetic valve application. However, the method may be applied generally to any application where a micro-cellular foam or pourous material, particularly an ePTFE membrane, needs to be placed over and around a radially expandable structural frame.
- Exemplary structural frames may include stents, stents grafts, valves (including percutaneously delivered venous valves), AAA (Abdominal Aortic Aneurysm) devices, local drug delivery devices, and the like. Accordingly, the disclosed device is not meant to limit the scope of the inventive method.
- a tubular structure is fabricated from a polymer material that can be processed such that it exhibits an expanded cellular structure, preferably expanded Polytetrafluoroethylene (ePTFE).
- ePTFE expanded Polytetrafluoroethylene
- the ePTFE tubing is made by expanding Polytetrafluoroethylene (PTFE) tubing, under controlled conditions, as is well known in the art. This process alters the physical properties that make it satisfactory for use in medical devices.
- PTFE Polytetrafluoroethylene
- the method comprises first placing a transfer sheath over a mandrel as shown in step 1000 .
- the transfer sheath is a thin material that is used to prevent the tubing and coating from adhering to the mandrel.
- the transfer sheath may be made of sheet metal, metal foil, or polymer sheet, such as for example Polytetrafluoroethylene (PTFE) .
- PTFE Polytetrafluoroethylene
- the transfer sheath will be made of a material that can be easily deformed, and preferably collapsed so that it can be withdrawn conveniently from the lumen of the tube once the process is complete.
- the transfer sheath/mandrel combination are then coated in a solution of highly elastic polymer, such as fluoroelastomer, as shown in step 1010 , to form an inner membrane.
- highly elastic polymer such as fluoroelastomer
- the coating may be applied using various methods, including, for example, spin coating, spray coating, dip coating, chemical vapor deposition, plasma coating, co-extrusion coating and insert molding.
- the coating solution comprises a polymer put into solution with a solvent, such as methanol.
- a solvent such as methanol.
- most solvents can be used with expanded Polytetrafluoroethylene (ePTFE).
- the polymer comprising the coating includes Daikin's Dai-El T630, a thermoplastic elastomer based on vinylidene fluoride/hexafluoropropylene/tetrafluoroethylene (VDF/HFP/TFE) and blends thereof.
- VDF/HFP/TFE vinylidene fluoride/hexafluoropropylene/tetrafluoroethylene
- other polymers such as siliconized polyurethanes and blends thereof, including Polymer Technology Group's Pursil, Carbosil, Purspan and Purspan F.
- the coating process should continue until the inner membrane achieves a wall thickness of between 6 ⁇ m and 100 ⁇ m or more, preferably between 12 ⁇ m to 25 ⁇ m.
- a polymer tube preferably an ePTFE tube
- a polymer tube may be expanded and placed over the sheath/mandrel combination (step 1015 ), before being contracted (step 1020 ).
- Expansion may be by any suitable expansion means known in the art, including mechanical expansion, such as by means of a balloon expansion device or expandable cage, expansion by utilizing a tapered mandrel (i.e. sliding the polymer tube over a tapered mandrel of increasing diameter) , etc.
- other means may be used in conjunction with the expansion means to assist placing the tube over the sheath mandrel combination. These assist means may include, for example, thermally expanding the tube with heat, or chemically expanding the tube with a solvent. These methods are known in the art.
- Contraction of the tube is typically done by reversing the method used to expand the tube. For example, where the tube is naturally elastic and expanded by a mechanical expansion means, removing the expansion means would allow the tube to contract towards it pre-expansion configuration. In addition the contraction of the tube may be enhanced by applying heat or chemicals (solvents).
- the whole assembly may be coated with a solution of highly elastic polymer, such as fluoroelastomer as shown in step 1025 to form the inner membrane.
- a solution of highly elastic polymer such as fluoroelastomer as shown in step 1025 to form the inner membrane.
- the coating process is similar to that shown in step 1010 above, and may be achieved by any method known in the art capable of achieving the desired result, including spin coating, spray coating, dip coating, chemical vapor deposition, plasma coating, co-extrusion coating and insert molding.
- step 1025 The coating process described in step 1025 should continue until the inner membrane described in the alternate embodiment is coated with a polymer base having a wall thickness of between 6 ⁇ m and 100 ⁇ m or more, preferably between 12 ⁇ m to 25 ⁇ m.
- the structural frame 101 is then radially expanded and positioned over the inner membrane as shown in step 1030 .
- the structural frame 101 may be radially expanded using any know expansion means, including a balloon expansion device or frame expansion device.
- the structural frame 101 is constructed from a shape memory alloy, such as Nitinol.
- Nitinol characteristically holds a deformed shaped when cooled, and returns to its original shape when heated. Accordingly, it is possible to hold a Nitinol structural frame 101 in the radially expanded state by cooling the frame before the expansion means is removed. This will facilitate placement of the Nitinol structural frame over the inner membrane.
- the structural frame 101 may then be radially contracted over the inner membrane, as shown in step 1040 . It is desirable to maintain a slight interference fit between the structural frame 101 and the inner membrane.
- the method to radially contract the structural frame 101 may depend on the material and type of construction of the structural frame 101 , and is not meant to limit the scope of the invention. As described above, a structural frame 101 constructed from a shape memory alloy, such as Nitinol, can be radially contracted (to the pre-expanded and cooled size) by heating. Depending on the material used, other methods that may also be employed to radially contract the structural frame include, simply removing the expansion means providing the radial expansion force, or applying a compressive force about the structural frame 101 . Still other methods to radially contract the structural frame 101 would be obvious to one of skill in the art.
- a second polymer tube preferably an ePTFE tube
- ePTFE tube is expanded and placed over the structural frame, as shown in step 1050 , forming an outer membrane.
- the tube is then contracted into position as shown in step 1060 .
- the tube may be expanded by several different means, including mechanical, thermal, or chemical (solvents) expansion.
- contraction of the tube may be accomplished by the methods described in step 1020 .
- each tube should have a wall thickness of between 25 ⁇ m and 50 ⁇ m before expansion; yielding a wall thickness of between 6 ⁇ m and 10 ⁇ m after expansion and placement. It should be noted that these membranes may or may not be bonded together. If only a single ePTFE tube is used for the outer membrane only, as described in step 1050 (not following alternate steps 1015 through 1025 ), the tube should have a wall thickness before expansion of between 50 ⁇ m and 100 ⁇ m; yielding a wall thickness after expansion of between 12 ⁇ m and 20 ⁇ m.
- the inner and outer membranes combine to form a membrane structure.
- the membrane structure would represent membrane tubular structure 400
- the structural frame would represent the structural frame 101 .
- the membrane structure may be optionally coated with a solution of a highly elastic polymer, such as a elastomeric polymer, as shown in step 1070 .
- the coating may be applied by any method known in the art, including spin coating, spray coating, dip coating, chemical vapor deposition, plasma coating, co-extrusion coating and insert molding.
- the coating solution may be a fluoroelastomer.
- the coating is Daikin G701BP, which is a 60/40% VDF/HFP.
- other materials having suitable characteristics might be used for the coating, for example, other polymers, such as siliconized polyurethane.
- the coating process should continue until the coating achieves a wall thickness of between 6 ⁇ m and 100 ⁇ m or more, preferably between 12 ⁇ m to 25 ⁇ m.
- the post processing step 1080 may be used to form or shape valve cusps, similar to cusps 404 , or valve flaps, such as flaps 403 , in the membrane structure.
- post processing may change the characteristics of the membrane structure by thickening or thinning the membrane in particular locations. Thickening the membrane may add rigidity and reinforcement to a particular area. Thinning the membrane may make the membrane more pliable.
- Still other post processing procedures may change the physical shape of the membrane structure, for example, by forming the loop collar 605 along the distal edge of membrane assembly 102 .
- the loop collar 605 may assist in controlling the translational and circumferential movement of the membrane assembly 102 along the valve struts 630 .
- the loop collars 605 may also reduce fatigue and tear stresses in the membrane.
- therapeutic or pharmaceutic agents may be added to any component of the device during fabrication, including, for example, the ESS fiber, polymer or coating solution, membrane tube, structural frame or inner and outer membrane, to treat any number of conditions.
- therapeutic or pharmaceutic agents may be applied to the device, such as in the form of a drug or drug eluting layer, or surface treatment after the device has been formed.
- the therapeutic and pharmaceutic agents may include any one or more of the following: antiproliferative/antimitotic agents including natural products such as vinca alkaloids (i.e.
- paclitaxel i.e. etoposide, teniposide
- antibiotics dactinomycin (actinomycin D) daunorubicin, doxorubicin and idarubicin
- anthracyclines mitoxantrone, bleomycins, plicamycin (mithramycin) and mitomycin
- enzymes L-asparaginase which systemically metabolizes L-asparagine and deprives cells which do not have the capacity to synthesize their own asparagine
- antiplatelet agents such as G(GP) ll b /lll a inhibitors and vitronectin receptor antagonists
- antiproliferative/antimitotic alkylating agents such as nitrogen mustards (mechlorethamine, cyclophosphamide and analogs, melphalan, chlorambucil), ethylenimine
- anticoagulants heparin, synthetic heparin salts and other inhibitors of thrombin
- fibrinolytic agents such as tissue plasminogen activator, streptokinase and urokinase), aspirin, dipyridamole, ticlopidine, clopidogrel, abciximab
- antimigratory antisecretory (breveldin)
- anti-inflammatory such as adrenocortical steroids (cortisol, cortisone, fludrocortisone, prednisone, prednisolone, 6 ⁇ -methylprednisolone, triamcinolone, betamethasone, and dexamethasone), non-steroidal agents (salicylic acid derivatives i.e.
- enolic acids piroxicam, tenoxicam, phenylbutazone, and oxyphenthatrazone
- immunosuppressives (cyclosporine, tacrolimus (FK-506), sirolimus (rapamycin), azathioprine, mycophenolate mofetil); angiogenic agents: vascular endothelial growth factor (VEGF), fibro
Abstract
The present invention relates to a medical device, and in particular, to a stent-based valve. The valve has a radially expandable structural frame having a substantially cylindrical configuration with first and second open ends and a longitudinal axis extending there between. The structural frame is formed from a lattice of interconnected elements and has a plurality of distal crowns. A biocompatible membrane assembly maintaining a substantially cylindrical shape about the longitudinal axis is attached to the structural frame such that the structural frame supports the biocompatible membrane assembly in a slack condition between the distal crowns.
Description
- This application claims the benefit under 35 U.S.C. 119(e) of U.S. Provisional Application Serial No. 60/379,604, filed May 10, 2002.
- The present invention relates to a medical device, and more particularly to a multi-lobed frame based unidirectional flow prosthetic valve, and the method for fabricating such valve.
- The human body has numerous biological valves that control fluid flow through body lumens and vessels. For example the circulatory system has various heart valves that allow the heart to act as a pump by controlling the flow of blood through the heart chambers, veins, and aorta. In addition, the venous system has numerous venous valves that help control the flow of blood back to the heart, particularly from the lower extremities.
- These valves can become incompetent or damaged by disease, for example, phlebitis, injury, or the result of an inherited malformation. Heart valves are subject to disorders, such as mitral stenosis, mitral regurgitation, aortic stenosis, aortic regurgitation, mitral valve prolapse and tricuspid stenosis. These disorder are potentially life threatening. Similarly, incompetent or damaged venous valves usually leak, allowing the blood to improperly flow back down through veins away from the heart (regurgitation reflux or retrograde blood flow). Blood can then stagnate in sections of certain veins, and in particular, the veins in the lower extremities. This stagnation of blood raises blood pressure and dilates the veins and venous valves. The dilation of one vein may in turn disrupt the proper function of other venous valves in a cascading manner, leading to chronic venous insufficiency.
- Numerous therapies have been advanced to treat symptoms and to correct incompetent valves. Less invasive procedures include compression, elevation and wound care. However, these treatments tend to be somewhat expensive and are not curative. Other procedures involve surgical intervention to repair, reconstruct or replace the incompetent or damaged valves, particularly heart valves.
- Surgical procedures for incompetent or damaged venous valves include valvuloplasty, transplantation, and transposition of veins. However, these surgical procedures provide somewhat limited results. The leaflets of some venous valves are generally thin, and once the valve becomes incompetent or destroyed, any repair provides only marginal relief.
- As an alternative to surgical intervention, drug therapy to correct valvular incompetence has been utilized. Currently, however, there are no effective drug therapies available.
- Other means and methods for treating and/or correcting damaged or incompetent valves include utilizing xenograft valve transplantation (monocusp bovine pericardium), prosthetic/bioprosthetic heart valves and vascular grafts, and artificial venous valves. These means have all had somewhat limited results.
- What is needed is an artificial endovascular valve for the replacement of incompetent biological human valves, particularly heart and venous valves. These valves may also find use in artificial hearts and artificial heart assist pumps used in conjunction with heart transplants.
- The present invention relates to a medical device, and in particular, to a frame-based valve. One embodiment of the invention comprises a radially expandable structural frame having a plurality of distal crowns or lobes. The structural frame is formed from a lattice of interconnected elements, and has a substantially cylindrical configuration with first and second open ends and a longitudinal axis extending there between. A tubular biocompatible membrane is coaxially disposed over at least a portion of the structural frame such that the structural frame supports the biocompatible membrane assembly in a slack condition between the distal crowns. The prosthetic valve may further have a valve strut attached to at least one of the distal crowns that extends in a distal direction substantially parallel to the longitudinal axis. The biocompatible membrane assembly may also extend in a distal direction past the distal crowns.
- In another embodiment of the invention, the prosthetic valve comprises a radially expandable structural frame having a plurality of articulating distal crowns. The structural frame is formed from a lattice of interconnected elements, and has a substantially cylindrical configuration with first and second open ends and a longitudinal axis extending there between. A tubular biocompatible membrane is coaxially disposed over at least a portion of the structural frame such that the structural frame supports the biocompatible membrane assembly in a slack condition between the distal crowns.
- In still another embodiment of the invention the prosthetic valve comprises a substantially cylindrical structural frame that has a hoop structure with a plurality of distal crowns. A substantially cylindrical biocompatible membrane assembly is attached to the structural frame such that the structural frame supports the biocompatible membrane assembly in a slack condition between the distal crowns.
- A prosthetic valve according to another embodiment of the invention has a radially expandable structural frame comprising a cylindrical hoop structure having a plurality of distal and proximal crowns, a proximal anchor, and one or more connecting members. The proximal anchor has a substantially cylindrical configuration and is formed from a lattice of interconnected elements. The one or more connecting members has a first and a second end, the first end of each connecting member is attached to the proximal anchor and the second end of each connecting member is attached to the hoop structure. A biocompatible membrane assembly is coaxially disposed over the structural frame and attached to the proximal anchor, such that the biocompatible membrane assembly extends distally along the one or more connecting members.
- FIG. 1 shows a perspective view of a prosthetic venous valve in the deployed state according to one embodiment of the present invention.
- FIG. 2A shows a perspective view of the prosthetic venous valve structural frame in the deployed state
- FIG. 2B shows a close-up perspective view of a loop having inner and outer radii according to one embodiment of the present invention.
- FIG. 3A shows a perspective view of a prosthetic valve having two hoop structures according to another embodiment of the present invention.
- FIG. 3B shows a perspective view of a structural frame having two hoop structures according to another embodiment of the present invention.
- FIG. 3C shows a perspective view of a structural frame having two hoop structures attached with bridge members.
- FIG. 3D shows a perspective view of a prosthetic venous valve having connecting members connected between the sinusoidal structure and proximal anchor according to one embodiment of the present invention.
- FIG. 3E shows a perspective view of the prosthetic venous valve structural frame having connecting members connected between the sinusoidal structure and proximal anchor in a peak-to-peak configuration according to one embodiment of the present invention.
- FIG. 4A is a perspective view illustrating one embodiment of the expanded (deployed) prosthetic venous valve assembly in the open position.
- FIG. 4B is a section view illustrating one embodiment of the expanded (deployed) prosthetic venous valve assembly in the open position.
- FIG. 5A is a perspective view illustrating one embodiment of the expanded (deployed) prosthetic venous valve assembly in the closed position.
- FIG. 5B is a section view illustrating one embodiment of the expanded (deployed) prosthetic venous valve assembly in the closed position.
- FIG. 6A is a perspective view of a prosthetic valve having flexible distal crowns capable of deflecting inward during retrograde blood flow.
- FIG. 6B is a perspective view of a prosthetic valve according to an embodiment of the present invention.
- FIG. 6C is a perspective view of a prosthetic valve having valve struts according to an embodiment of the present invention.
- FIG. 6D is a perspective view illustrating a membrane limiting means according to one embodiment of the present invention.
- FIG. 6E is a perspective view illustrating a membrane limiting means according to one embodiment of the present invention.
- FIG. 6F is a perspective view illustrating a membrane limiting means according to one embodiment of the present invention.
- FIG. 6G is a perspective view of a prosthetic valve having valve struts according to an embodiment of the present invention.
- FIG. 7 is a flow diagram illustrating the steps to electro-statically spin a tubular membrane on a structural frame according to one embodiment of the present invention.
- FIG. 8A is section view illustrating the expanded (deployed) prosthetic venous valve assembly in the open position after some post processing according to one embodiment of the present invention.
- FIG. 8B shows a close-up section view illustrating a portion of the valve assembly after some post processing according to one embodiment of the present invention.
- FIG. 9 is a flow diagram illustrating the steps to electro-statically spin a tubular membrane on a structural frame according to one embodiment of the present invention.
- FIG. 10 is a flow diagram illustrating the steps to place a tubular membrane over a structural frame according to one embodiment of the present invention.
- The stent-based valves of the present invention provide a method for overcoming the difficulties associated with the treatment of valve insufficiency. Although stent based venous valves are disclosed to illustrate one embodiment of the present invention, one of ordinary skill in the art would understand that the disclosed invention can be equally applied to other locations and lumens in the body, such as, for example, coronary, vascular, non-vascular and peripheral vessels, ducts, and the like, including but not limited to cardiac valves, venous valves, valves in the esophagus and at the stomach, valves in the ureter and/or the vesica, valves in the biliary passages, valves in the lymphatic system and valves in the intestines.
- In accordance with one aspect of the present invention, the prosthetic valve is designed to be percutaneously delivered through a body lumen to a target site by a delivery catheter. The target site may be, for example, a location in the venous system adjacent to an insufficient venous valve. Once deployed the prosthetic venous valve functions to assist or replace the incompetent or damaged natural valve by allowing normal blood flow (antegrade blood flow) and preventing or reducing backflow (retrograde blood flow).
- A perspective view of a prosthetic venous valve in the expanded (deployed) state according to one embodiment of the present invention is shown in FIG. 1. The prosthetic
venous valve 100 comprises astructural frame 101 and abiocompatible membrane assembly 102. - In one embodiment, the
membrane assembly 102 is comprised of a tubular membrane, valve flaps and valve cusps. The flaps and cusps may be independent components attached to the tubular membrane to form themembrane assembly 102, but are preferably part of, and integrated into, the tubular membrane. In a preferred embodiment, the valve flaps and valve cusps are formed into the tubular membrane by processing techniques as will be discussed in greater detail below. - For clarity, a perspective view of the
structural frame 101 according to one embodiment of the present invention is shown in FIG. 2A. Thestructural frame 101 consists of a stent based sinusoidal structure, having asingle hoop section 200A with one or more proximal and distal crowns (lobes) 205, 206 respectively. In a preferred embodiment, at least threedistal crowns 206 are utilized as illustrated. However, this configuration is not meant to limit the scope of the invention. Various other configurations having one or moredistal crowns 206 may be used, and would be understood by one of skill in the art. - It should be noted that the terms proximal and distal are typically used to connote a direction or position relative to a human body. For example, the proximal end of a bone may be used to reference the end of the bone that is closer to the center of the body. Conversely, the term distal can be used to refer to the end of the bone farthest from the body. In the vasculature, proximal and distal are sometimes used to refer to the flow of blood to the heart, or away from the heart, respectively. Since the prosthetic valves described in this invention can be used in many different body lumens, including both the arterial and venous system, the use of the terms proximal and distal in this application are used to describe relative position in relation to the direction of fluid flow. For example, the use of the term proximal crown in the present application describes the upstream crown of
structural frame 101 regardless of its orientation relative to the body. Conversely, the use of the term distal crown is used to describe the down stream crown onstructural frame 101 regardless of its orientation relative to the body. Similarly, the use of the terms proximal and distal to connote a direction describe upstream (retrograde) or downstream (antegrade) respectively. - As previously disclosed, in one embodiment of the invention, the structural frame is a stent-based structure. This configuration facilitates the percutaneous delivery of the prosthetic
venous valve 100 through the vascular system in a compressed state. Once properly located, the stent-basedvenous valve 100 may be deployed to the expanded state. - The sinusoidal stent based structural frame illustrated in FIG. 2A is shown having an S shaped pattern. This configuration is shown for the purpose of example, and is not meant to be construed as limiting the scope of the invention. One of ordinary skill in the art would understand that other stent geometries having similar crowns may be used.
- The sinusoidal stent based
structural frame 101 comprises a tubular configuration of structural elements having proximal and distal open ends and defining alongitudinal axis 106 extending there between. Thestructural frame 101 has a first diameter (not shown) for insertion into a patient and navigation through the vessels, and a second diameter D2 for deployment into the target area of a vessel, with the second diameter being greater than the first diameter. Thestructural frame 101, and thus the stent basedvenous valve 100, may be either a mechanical (balloon) or self-expanding stent based structure. - The
structural frame 101 comprises at least onehoop structure 200A extending between the proximal and distal ends. Thehoop structure 200A includes a plurality of longitudinally arranged strut members 208 and a plurality ofloop members 210 connecting adjacent struts 208. Together, these strut members 208 andloop members 210 form the proximal anddistal crowns loops 210 have a substantially semi-circular configuration, having aninner radii 212 andouter radii 214, and are substantially symmetric about their centers. The inner andouter radii - The embodiment of the invention illustrated in FIGS. 1 and 2 show a
structural frame 101 having asingle hoop structure 200A. However, it should be understood that this configuration is not meant to be construed as a limiting feature, and other configurations having a plurality of hoop structures are also contemplated by the present invention. - FIGS. 3A through 3C illustrate a
structural frame 101 having twohoop structures 200A and 200B according to another embodiment of the present invention. FIG. 3A shows a completeprosthetic valve 300 in the expanded (deployed) position, illustrating both thestructural frame 101 andmembrane assembly 102. For clarity, FIG. 3B is an illustration of just thestructural frame 101 without themembrane assembly 102. In the illustrated embodiment, thehoop structures 200A and 200B are rigidly attached at complimentary points along their respective outer radii of theloops 210. - In an alternate embodiment shown in FIG. 3C, the
hoop structures 200A, 200B may be attached with one ormore bridge members 305. Eachbridge member 305 comprises two ends 316A, 316B. One end 316A, 316B of eachbridge 305 is attached to one loop on one hoop. Usinghoop sections 200A and 200B for example, eachbridge member 305 is connected at end 316A toloop 210 onhoop section 200A at apoint 320. Similarly, the opposite end 316B of each bridge member 314 is connected toloop 210 on hoop sections 200B at apoint 321. - In any of the above described configurations, the connections between the
hoop structures 200A, 200B etc. may be made at everyloop member 210 around the circumference of the structure; or alternatively, at a subset of theloop members 210 around the circumference of the structure. In other words, connectedloop members 210 alternate with unconnected loop members in some defined pattern. - Depending on the location of the implanted valve, it may be desirable to attach the hoop structures to an anchor by means of one or more connecting members. This configuration may add to the stability of the implanted valve. The anchor may be in the form of another sinusoidal stent based structure, such as the structures depicted in FIGS. 1 through 3C. However, any radially expandable structural frame that can aid in anchoring prosthetic valve is contemplated by the present invention. These anchors may be located downstream (proximal) or upstream (distal) from the lobed valve.
- FIG. 3D illustrates a prosthetic
lobed valve 300 incorporating a proximal anchor and connecting members according to one embodiment of the invention. For clarity, FIG. 3E shows thevalve 300structural frame 101 with themembrane structure 102 removed. The illustratedvalve 300 comprises asingle hoop structure 200A having proximal anddistal crowns anchor 315 proximal to thehoop structure 200A. - The
anchor 315 illustrated in FIGS. 3D and 3E is structurally similar to the sinusoidal stent based structure comprising thehoop structure 200A. Theanchor 315 comprises a tubular configuration of structural elements having proximal and distal open ends and defining alongitudinal axis 306 extending there between. Thestent anchor 315 has a first diameter (not shown) for insertion into a patient and navigation through the vessels, and a second diameter D2 for deployment into the target area of a vessel, with the second diameter being greater than the first diameter. Thestent anchor 315, and thus the stent basedvenous valve 300, may be either a mechanical (balloon) or self-expanding stent based structure. - The
stent anchor 315 comprises at least onehoop structure 336 extending between the proximal and distal ends. Thehoop structure 336 includes a plurality of longitudinally arrangedstrut members 338 and a plurality ofloop members 340 connectingadjacent struts 338. As shown, thestent anchor 315 has three hoop structures. -
Adjacent struts 338 are connected at opposite ends in a substantially S or Z shaped pattern so as to form a plurality of cells. As previously discussed, one of ordinary skill in the art would recognize that the pattern shaped by the struts is not a limiting factor, and other shaped patterns may be used. The plurality ofloops 340 have a substantially semi-circular configuration, having an inner radii and outer radii, and are substantially symmetric about their centers. - The connecting
member 310 may be connected to thehoop structure 200A (on the sinusoidal valve structure) and theproximal anchor 315 at various points along the structures. As illustrated in FIG. 3E, the connectingmembers 310 are connected between the proximal end of thehoop structure 200A and the distal end of theproximal anchor 315 at the inflection point of the loop members. This configuration creates a “Peak-to-Peak” connection bridging the outer radii of the inflection point ofloop members 210 on thehoop structure 200A with the outer radii of the inflection point of theloop member 340 on theproximal anchor 315. - Preferably the connecting
members 310 are connected to the inflection point ofloop members - Alternatively, the connecting
members 310 may be connected between thehoop structure 200A andproximal anchor 315 to create a “Peak-to-Valley” connection between theloop members members 310 are connected to the proximal end of thehoop structure 200A at the outer radii of the inflection point ofloop member 210, and the inner radii of the inflection point ofloop member 340 on the proximal end of theproximal anchor 315. - In a further embodiment (not shown), the connecting
members 310 may be connected between the distal end of thehoop structure 200A and the proximal end of theproximal anchor 315 at the inflection point of theloop members loop members 340 on theproximal anchor 315 with the inner radii of the inflection point of theloop member 210 on thehoop structure 200A. - In still a further embodiment (not shown), the connecting
members 310 may be connected between the strut members 208 of thehoop structure 200A and thestrut members 338 of theproximal anchor 315. - In any of the above described configurations, the connections between the connecting
members 310 and thehoops 200 may be made at every inflection point around the circumference of the structure; or alternatively, at a subset of the inflection points around the circumference of the structure. In other words, connected inflection points alternate with unconnected inflection points in some defined pattern. - As earlier described, the connecting
members 310 are attached between the sinusoidal stent based structure (havingloop 200A in FIGS. 3D and 3E) and theproximal anchor 315 to further support the biocompatible membrane assembly 102 (not shown in FIG. 3E). In one embodiment, the connectingmembers 315 are substantially straight members, connecting thehoop structure 200A andproximal anchor 315 in a direction substantially parallel to thelongitudinal axis 306. Although three connectingmembers 315 are shown in the illustrated embodiment, one of skill in the art would understand that one or more connecting members may be used. - Alternatively, the connecting
members 315 may be twisted in a helical fashion as they extend from thehoop structure 200A to the proximal anchor 315 (not shown). Specifically, the connection points between the connectingmembers 315 and thehoop structure 200A, and the connecting members 105 and theproximal anchor 315, are rotationally phased 180 degrees from each other to provide the helical design. - Each connecting
member 310 may also be biased inward slightly toward thelongitudinal centerline 306, creating astructural frame 101 having an hour-glass shape with the minimum radius located substantially at the longitudinal midpoint along the connectingmember 310 length (not shown). The proximal crowns 205 may similarly be biased inward. This configuration may assist theprosthetic valve 300 when closing by forming larger valve cusps. - The materials for the
structural frame 101 should exhibit excellent corrosion resistance and biocompatibility. In addition, the material comprising thestructural frame 101 should be sufficiently radiopaque and create minimal artifacts during MRI. - The present invention contemplates deployment of the prosthetic
venous valve 100 by both assisted (mechanical) expansion, i.e. balloon expansion, and self-expansion means. In embodiments where the prostheticvenous valve 100 is deployed by mechanical (balloon) expansion, thestructural frames 101 is made from materials that can be plastically deformed through the expansion of a mechanical assist device, such as by the inflation of a catheter based balloon. When the balloon is deflated, theframe 101 remains substantially in the expanded shape. Accordingly, the ideal material has a low yield stress (to make theframe 101 deformable at manageable balloon pressures), high elastic modulus (for minimal recoil), and is work hardened through expansion for high strength. The most widely used material for balloonexpandable structures 101 is stainless steel, particularly 316L stainless steel. This material is particularly corrosion resistant with a low carbon content and additions of molybdenum and niobium. Fully annealed, stainless steel is easily deformable. - Alternative materials for mechanically expandable
structural frames 101 that maintain similar characteristics to stainless steel include tantalum, platinum alloys, niobium alloys, and cobalt alloys. In addition other materials, such as polymers and bioabsorbable polymers may be used for thestructural frames 101. - Where the prosthetic
venous valve 100 is self-expanding, the materials comprising thestructural frame 101 should exhibit large elastic strains. A suitable material possessing this characteristic is Nitinol, a Nickel-Titanium alloy that can recover elastic deformations of up to 10 percent. This unusually large elastic range is commonly known as superelasticity. - The disclosure of various materials comprising the structural frame should not be construed as limiting the scope of the invention. One of ordinary skill in the art would understand that other material possessing similar characteristics may also be used in the construction of the prosthetic
venous valve 100. For example, bioabsorbable polymers, such as polydioxanone may also be used. Bioabsorbable materials absorb into the body after a period of time, leaving only thebiocompatible membrane 102 in place. The period of time for thestructural frame 101 to absorb may vary, but is typically sufficient to allow adequate tissue growth at the implant location to adhere to and anchor thebiocompatible membrane 102. - The
structural frame 101 may be fabricated using several different methods. Typically, thestructural frame 101 is constructed from sheet, wire (round or flat) or tubing, but the method of fabrication generally depends on the raw material form used. - The
structural frame 101 can be formed from wire using convention wire forming techniques, such as coiling, braiding, or knitting. By welding the wire at specific locations a closed-cell structure may be created. This allows for continuous production, i.e. the components of thestructural frame 101 may be cut to length from a long wire mesh tube. - In addition, the complete frame structure may be cut from a solid tube or sheet of material, and thus the
structural frame 101 would be considered a monolithic unit. Laser cutting, water-jet cutting and photochemical etching are all methods that can be employed to form thestructural frame 101 from sheet and tube stock. - As discussed above, the disclosure of various methods for constructing the
structural frame 101 should not be construed as limiting the scope of the invention. One of ordinary skill in the art would understand that other construction methods may be employed to form thestructural frame 101 of the prostheticvenous valve 100. - The
structural frame 101 is radially expandable and assists in securing theprosthetic valve 100 to the inside wall of a body vessel such as a vein. Once deployed in the desired location, radially expandable structural frame (and thus the prosthetic valve 100) will expand to an outside diameter slightly larger that the inside diameter of the native vessel (not shown) and remain substantially rigid in place, anchoring the valve assembly to the vessel. - The membrane assembly is formed from a flexible membrane-like biocompatible material that is affixed to the
frame structure 101. The membrane must be strong enough to resist tearing under normal use, yet thin enough to provide the necessary flexibility that allows thebiocompatible membrane assembly 102 to open and close satisfactorily. - FIGS. 4A and 4B are perspective and section views, respectively, illustrating one embodiment of the expanded (deployed) prosthetic
venous valve assembly 100 in the open position. The membrane material may be a biological material, such as a vein or small intestine submucosa (SIS), but is preferably a synthetic material such as a polymer, for example an elastic or elastomeric polymer, including a fluoropolymer, fluoroelastomer, or a bioabsorbable material, such as a bioabsorbable polymer or bioabsorbable elastomer. Bioabsorbable materials may allow cells to grow and form a tissue membrane (or valve flaps) over the bioabsorbable membrane. The bioabsorbable membrane then absorbs into the body, leaving the tissue membrane and/or flaps in place to act as a new natural tissue valve. - To achieve the necessary flexibility and strength of the
membrane assembly 102, the synthetic material may be reinforced with a fiber, such as an electro-statically spun (ESS) fiber, porous foam, such as ePTFE, or mesh. The flexible membrane like biocompatible material is formed into a tube (membrane tubular structure 400) placed over and around thestructural frame 101. The membranetubular structure 400 has a first (distal) and second (proximal) ends 401, 402 respectively, and preferably also has integrated valve flaps 403 andvalve cusps 404. These components together comprise themembrane assembly 102. - The
first end 401 of the membranetubular structure 400 is located at and between the distal crowns 206. Thesecond end 402 of the membranetubular structure 400 is preferably located proximal to at least one half of the most proximal hoop structure, e.g. 200B in FIG. 3B. In one embodiment of the invention, themembrane structure 400 completely covers the proximal most hoop structure to the proximal crowns 205. This configuration allows thestructural frame 101 to expand the membranetubular structure 400 into the native vessel wall, anchoring the membranetubular structure 400 in place, and providing adequate sealing against retrograde blood flow. - The
distal end 401 of the membranetubular structure 400 terminates with the valve flaps 403. The number of valve flaps 403 is directly proportional to the number ofdistal crowns 206 supporting themembrane tubular assembly 102. Preferably, the design of the valve flaps 403, and for thatmatter valve cusps 404, are such that thetubular membrane structure 400 between the distal crowns in not tightly drawn or taut. This “slack” facilitates closing the valve by allowing thevalve cusps 404 to act as pockets that fill during retrograde flow. Conversely, during antegrade flow, the additional slack in thetubular membrane structure 400 is pushed to the vessel wall, allowing blood to flow through the valve leaflets. - The valve flaps403 are sufficiently pliable and supple to easily open and close as the blood flow changes from antegrade to retrograde. When the valve flaps 403 close (during retrograde flow) the interior surfaces of the
flaps 403 and/or membranetubular structure 400 come into contact to prevent or adequately reduce retrograde blood flow. - As earlier disclosed, to facilitate closing the valve flaps403 during retrograde blood flow,
valve cusps 404 are formed into the membranetubular structure 400. Thevalve cusps 404 are defined generally by the intersection of thedistal crowns 206 and membranetubular structure 400, and are preferably formed at least in part by the slacktubular membrane 400 between the distal crowns 206. - The use of the term “cusps” is not meant to limit the scope of this invention. Although the term “cusps” is often more aptly used to describe the valve members in semilunar valves, such as the aortic and pulmonary valves, this discussion refers to both the cusps of semilunar valves and the “leaflets” of venous and atrioventricular valves. Accordingly, it should be understood that the aspects discussed in relation to these valves could be applied to any type of mammalian valve, including heart valves, venous valves, peripheral valves, etc.
- During retrograde flow, blood passes the leading edge of valve flaps403 and enters the
valve cusps 404. Since the membrane tubular structure 400 (and membrane assembly 102) are substantially sealed against the inner vessel wall by thestructural frame 101, thevalve cusps 404 form a substantially fluid tight chamber. As thevalve cusps 404 fill, the membranetubular structure 400 is directed inward until the interior surfaces of the membranetubular structure 400 contact each other, particularly along the leading edges of valve flaps 403, closing themembrane assembly 102. FIGS. 5A and 5B show perspective and section views, respectively, illustrating one embodiment of the expanded (deployed) prostheticvenous valve assembly 100 in the closed position. - In another embodiment of the invention, the
distal crowns 206 are flexible and capable of deflecting inward during retrograde blood flow, further assistingvalve 100 when closing and opening. A perspective view illustrating an example of this embodiment is shown in FIG. 6A. As illustrated flexibledistal crown 606 articulate inward indirection 608 to assist closing thevalve 100. The flexibledistal crowns 606 may pivot along apivot line 610 as shown, or gradually bend inward along their length. - In a preferred embodiment of the invention, the
membrane assembly 102 is normally configured in the open position, and only moves to the closed position upon retrograde blood flow. This configuration minimizes interference with blood flow (minimized blocking) and reduces turbulence at and through the valve. The flexibledistal crowns 606 in this embodiment have an inferior radial stiffness, and provide a natural bias against the movement of themembrane assembly 102 to the closed position. This bias assists the valve flaps 403 andvalve cusps 404 when returning to the open position. - Depending on the application, it may also be desired that the bias towards opening the membrane assembly102 (against closing) be sufficiently high to commence opening the valve before antegrade blood flow begins, i.e. during a point in time when the blood flow is stagnant (there is neither antegrade nor retrograde blood flow), or when minimal retrograde flow is experienced.
- In other applications, it may be desirable to have the valve assembly normally configured in the closed position, biased closed, and only open upon antegrade flow.
- In a further embodiment, the
valve membrane assembly 102 may extend past the distal end of thestructural frame 101, i.e. pastdistal crowns 206, in a distal direction as shown in FIG. 6B. During retrograde blood flow, theextended section 602 ofvalve membrane 102 will collapse upon itself, thus limiting or preventing fluid flow back through the valve. In such embodiments, thevalve membrane 102 distal the structural frame 101 (i.e. membrane section 602) is of sufficient rigidity to prevent themembrane 102 from collapsing in through thestructural frame 101 and inverting. Rigidity may be provided by insertingstructural elements 620 into themembrane assembly 102 as shown in FIG. 6B. Alternatively, themembrane assembly 102 may have ribs or thickened sections processed into the membrane to provide sufficient rigidity. - In another embodiment of the present invention, one or more valve struts may extend distally from the end of the
structural frame 101 providing rigidity sufficient to support thevalve membrane 102, particularlymembrane section 602 from inverting. These valve struts may be an integral part of thestructural frame 101, and made from similar material. - FIG. 6C illustrates a
valve 100 having valve struts 630 according to one embodiment of the present invention. In the embodiment shown, the valve struts 630 extend from the distal end of thestructural frame 101, in particular, from theoutside radii 214 of thedistal crown 206 comprising thehoop structure 200A. In an alternate embodiment, thevalve strut 630 may extend from theinside radii 212 of theproximal crown 205 comprising thehoop structure 200A. This alternate embodiment is shown in FIG. 6G. Still other embodiments having different connection points would be understood by one of skill in the art. - Although three valve struts630 are shown for illustrative purposes, this exemplary embodiment is not meant to limit the scope of the invention. One of skill in the art would understand that one or more valve struts may be used and still accomplish the general intent of the invention.
- As earlier described, the
membrane assembly 102 is made from a flexible membrane-like biocompatible material formed into the membranetubular structure 400. Themembrane 400 can be woven, non-woven (such as electrostatic spinning), mesh, knitted, film or porous film (such as foam). - The
membrane assembly 102 may be fixedly attached to the structural frame by many different methods, including attachment resulting from radial pressure of thestructural frame 101 against themembrane assembly 102, attachment by means of a binder, heat, or chemical bond, and/or attachment by mechanical means, such as welding, suturing or coating. Preferably some of themembrane assembly 102, such asdistal end 402 oftubular membrane 400, is slideably attached to thestructural frame 101, particularly along valve struts 630. Allowing thedistal end 401 to slide along the valve struts 630 may allow or improve the opening and closing of theflaps 403. The sliding movement may also assist thecusps 404 when filling and emptying. - In some applications, excessive sliding movement of the
membrane assembly 102 is undesirable. In these embodiments, a limiting device may be integrated into theprosthetic valve 100 to limit the sliding movement of themembrane assembly 102. Examples of limiting devices are shown in FIGS. 6D to 6F. In each embodiment a stop 600 (illustrated asstop membrane assembly 102 is wrapped around the valve struts 630 and bonded to itself to form aloop collar 605. Theloop collar 605 must be sized to inhibit thedistal end 402 of themembrane assembly 102 from sliding past the stop 600. In FIG. 6D, the valve struts 630 has a thickened or “bulbous”section forming stop 600A. FIG. 6E illustrates an undulatingstop 600B configuration. Similarly, FIG. 6F shows thestop 600C configured as a double bulbous section. It should be noted that the various configurations illustrated in FIGS. 6D through 6F are exemplary. One of ordinary skill in the art would understand that other configurations of stops may used. - In one embodiment of the invention the
tubular membrane 400 is manufactured from a fiber reinforced elastomer, such as an elastomeric fluoropolymer. The elastomer allows thetubular membrane 400 to be extremely thin and elastic, while the fiber provides the necessary strength. One method used to produce this type of reinforced membrane valve is an Electro-Static Spinning (ESS) process. Alternatively, a reinforcing fiber may be would around thestructural frame 101, and an ESS membrane formed over the reinforcing fiber andstructural frame 101. - The ESS process can be used to form a tubular membrane on many different types of structural frames, including frames associated with stents, stent grafts, valves, including percutaneously delivered venous valve, AAA (Abdominal Aortic Aneurysm) devices, local drug delivery devices, and the like. The disclosure of the ESS process for forming the
tubular membrane 400 on the structural frame of a stent-based venous valve is exemplary, and thus not meant to limit the scope of this invention. - FIG. 7 shows the steps for electro-statically spinning a reinforced tubular membrane onto a structural frame according to one embodiment of the present invention. The ESS process comprises first placing a transfer sheath over a spinning mandrel as shown in
step 700. The transfer sheath is a thin material that is used to prevent the ESS spun fiber from adhering to the mandrel. In instances where the mandrel itself is not electrically conducting, the transfer sheet may also provide the necessary electrical conductivity to attract the ESS spun fiber. - In one embodiment of the invention, the transfer sheath comprises a thin polymer tube, preferably fluoropolymer, of such a thickness that it can be easily deformed, and preferably collapsed, so that it is capable of being withdrawn conveniently from the lumen of the
structural frame 101 and/or membranetubular structure 400. The use of a transfer sheath made of other fibrous or sheet materials, such as other polymer, polymeric or metallic materials is not excluded. Most preferably, the transfer sheath will be made of an ePTFE tube. - To enhance electrical conductivity and reduce the time it takes to build up the ESS layer, the ePTFE tube may be first coated with gold on at least a portion of the interior surface before placing the tube on the mandrel. This process may be completed by coating the inside of the tube, but is preferably done by coating the exterior of the ePTFE tube and then inverting the tube so that the gold coating is on the interior surface. The process may also be completed by inverting the tube so that the interior surface to be coated is exposed on exterior of the tube, coating the now exposed interior surface, and the inverting the tube so that the interior coated surface is back on the inside of the tube.
- It should be noted that under certain circumstances it may not be necessary to use the transfer sheath. Such circumstances may include, for example, where the spinning mandrel is electro-statically conducting and has a surface or surface treatment that will prevent the ESS spun fiber from adhering to the mandrel.
- In a preferred embodiment, the spinning mandrel is electrically conducting, and more preferably, is a metal coated with Teflon®. However, electrical conduction may not be essential. In such embodiments the spinning mandrel may be of any suitable material, including plastic material. Non-conductors may be used so long as the charge is capable of being transferred (i.e. bleed off) onto the transfer sheet or through the material itself.
- The spinning mandrel may be hollow or solid, and preferably has a smooth surface to facilitate sliding between the transfer sheath and mandrel during removal. However, it may be desirable to maintain some degree of frictional resistance between the transfer sheath and mandrel to reduce slippage between the two components during the ESS process.
- The valve
structural frame 101 is then placed on the transfer sheath,step 710, and the ESS fiber is spun directly onto the valvestructural frame 101 as shown instep 720. Preferably, thestructural frame 101 is configured in the expanded or deployed state prior to placing thestructural frame 101 on the spinning mandrel. This is generally the case when thestructural frame 101 is of the self-expanding design. In other embodiments, such as balloon-expandable designs, the expansion mechanism may be integrated within the spinning mandrel to expand the structural frame during the spinning process. - The expandable mandrel may also be used for electro-statically spinning a fiber onto a self-expanding
structural frame 101. In such instances, the self-expandingstructural frame 101 is placed on the spinning mandrel in the expanded state, and the expansion mechanism on the expandable mandrel is mandrel activated to further radially expand the structural frame to a “super-expanded” state. ESS fiber is then spun directly onto the super-expandedstructural frame 101. The larger diameter of the super-expandedstructural frame 101 allows more material to be deposited on the structural frame, creating slack between the distal crowns, which may result in less post processing procedures. Post processing is described instep 760. - Electro-static spinning of a fiber is generally known in the art, and typically involves creating an electrical potential between a source component, i.e. the fiber or preferably a fiber forming liquid, and a downstream component, i.e. the spinning mandrel, transfer sheath or structural frame. The electrical potential causes the source component, typically the fiber forming liquid, to be attracted to, and thus move towards, the downstream component.
- The electrical potential is created by providing an electrical charge to either the source or downstream component, and grounding the other component. Preferably, the source component will receive an electrical charge, while the downstream component is grounded.
- Many different methods are known in the art for producing an electrical charge on a source component. In one embodiment, a fiber forming liquid is introduced into an electric field, whereby the fiber forming liquid is caused to produce a charged fiber. In another, more preferred embodiment, a device (introducer device) introducing the fiber forming liquid into the process is electrically charged, thus causing the fiber forming liquid to assume a like charge.
- Several methods may be used to introduce the fiber forming liquid into the process, including spraying the fiber forming liquid from a nozzle, or injecting the fiber forming liquid from a needle, orifice or drip tube. In a preferred embodiment, the fiber forming liquid is sufficiently viscous to be extruded into the process with an extrusion device.
- Once the fiber forming liquid is introduced into the process, it is hardened to form the ESS fiber. Hardening of the liquid into an ESS fiber may be accomplished, for example, by cooling the liquid until the fiber forming liquid will not lose its fibrous shape. Other methods for hardening the fiber may also include hardening by introducing a chemical hardener into the fiber forming liquid, or directing an air stream over the electrically drawn fiber forming liquid stream. In a preferred embodiment, a polymer is put into solution with a solvent to form a viscous fiber forming liquid. As the fiber forming liquid is drawn from the introducer device, the solvent comes out of solution forming the polymer fiber.
- Various drying techniques may be applied to evaporate the solvent and bring the polymer out of solutions. Drying techniques may include, for example, applying heat or airflow to or over the coated fiber spun frame assembly. In addition, the solvent may dry naturally without applying artificial drying techniques.
- The viscosity of the fiber forming liquid may be adjusted based on the material used for the source component, and the percent solids desired as the source component reaches the downstream component. Typical concentrations range from 2 to 100 percent. The choice of concentration depends on the material, its molecular weight, the solvent efficiency, and temperature. The concentration and temperature also control the diameter of the fiber. These viscosities will typically produce a fiber at the downstream component having percent solids in the range of about 95 percent to about 100 percent, and preferably over 99 percent. This is desirable in order to produce structures that contain entangled or point bonded fibers. Concentrations lower than 95 percent can be used if it is desired to allow filaments to fuse together into a sheet-like barrier structure.
- The hardened fiber is then collected onto the structural frame. Collecting of the fiber involves attracting the ESS fiber to the downstream component (i.e. spinning mandrel, transfer sheath or structural frame) of the ESS system, while spinning the downstream component. In a preferred embodiment, where the source component is electrically charged, a downstream component is grounded to complete the electric potential between the source and downstream component, and thus attract the ESS fiber. In other embodiments, a downstream component may be electrically charged to attract the ESS fiber where the source component is grounded. In still other embodiments, various combinations of downstream components may be electrically charged to enhance electrical conductivity and reduce the time it takes to build up the ESS layer.
- Particular ESS fibers suitable for this spinning process include fluoropolymers, such as a crystalline fluoropolymer with an 85/15% (weight/weight ratio) of vinylidene fluoride/hexafluoropropylene (VDF/HFP). Solvay Solef® 21508 and Kynarflex 2750-01 are two such examples. However, one of skill in the art would understand that any material possessing the desired characteristics may be used, including, for example: bioabsorbable polymers, such as polyglycolic acid, polylactic acid, poly (paradioxanone), polycaprolactone, poly (trimethylenecarbonate) and their copolymers; and semicrystalline bioelastomers, such as 60/40% (weight/weight ratio) of polylactic acid/polycaprolactone (PLA/PCL), 65/35 (weight/weight ratio) of polyglycolic acid/polycaprolactone (PGA/PCL), or nonabsorbable siliconized polyurethane, non-siliconized polyurethanes, siliconized polyureaurethane, including siliconized polyureaurethane end capped with silicone or fluorine end groups, or natural polymers in combination thereof. It should be noted that poly(trimethylenecarbonate) can not be spun as a homopolymer.
- The spinning process should be continued until an ESS fiber tube, or fabric, is formed having a wall thickness of between 5 μm and 100 μm or more, preferably, approximately 20 μm. The ESS fiber spun
structural frame 101 is then removed from the spinning mandrel,step 730, before the transfer sheath is removed from the fiber spun frame,step 740. Once this step is completed, the fiber spun structural frame is coated in a solution of polymer, such as fluoroelastomer, as shown instep 750. - Several different methods may be utilized to perform the coating process on the fiber spun structural frame, including spray coating with an air or airless sprayer, dip coating, chemical vapor deposition, plasma coating, coextrusion coating, spin coating and insert molding. In still another preferred embodiment, the fiber spun structural frame is first dip coated in a polymer solution, and then spun about its longitudinal axis to more evenly distribute the coating. In this embodiment, the fiber spun structural frame is not first removed from the spinning mandrel. Instead, the frame/mandrel assembly is dip coated and spun before removing the fiber spun structural frame from the spinning mandrel. Still other methods for coating the fiber spun structural frame would be obvious to one of skill in the art.
- The coating process may act to encapsulate and attach at least a portion of the spun ESS reinforcement fiber to the
structural frame 101. It should be noted that it in some embodiments of the invention, some movement between themembrane assembly 102 and thestructural frame 101 is desired. Accordingly, not all of the ESS fiber spun structural frame may be coated. - The coating process may also remove some porosity of the membrane material. However, it may be desirable to maintain some porosity in particular embodiments to promote biological cell grown on and within the membrane tubular structure.
- The coating solution preferably comprises a polymer put into solution with a solvent. As the solvent evaporates, the polymer comes out of solution forming the coating layer. Accordingly, for the process to work properly, the solvent used in the coating solution should not dissolve or alter the ESS fibers being coated. By way of example, a coating solution of 60/40% VDF/HFP in methanol (methanol being the solvent) has been found to be a suitable solution for coating an ESS fiber comprised of 85/15% VDF/HFP.
- In one embodiment of the invention, the polymer comprising the coating is Daikin's Dai-El G701BP, which is a 60/40% VDF/HFP. In addition, Daikin's Dai-El T630, a thermoplastic elastomer based on vinylidene fluoride/hexafluoropropylene/tetrafluoroethylene (VDF/HFP/TFE) can also be used. Again, one of ordinary skill in the art would understand that other materials having suitable characteristics may be used for the coating, for example, other polymers, such as siliconized polyurethane, including Polymer Technology Group's Pursil, Carbosil, Purspan and Purspan F.
- The coating process may be repeated until the desired characteristics and thickness are achieved. For venous valves a thickness of between 12 μm and 100 μm and preferably between 25 μm and 50 μm has been found to be acceptable.
- Once the coating process is complete some post processing of the membrane
tubular structure 400 may take place to achieve particular desired characteristics or configurations. This may include creating the final form of themembrane assembly 102. The post processing step is shown asoptional step 760 in FIG. 7. - The
post processing step 760 may be used to form or shape, for example, a valve cusp, similar tocusp 404, in the membranetubular structure 400. In addition, post processing may change the characteristics of the membranetubular structure 400 by thickening or thinning the membrane in particular locations. Thickening the membrane may add rigidity and reinforcement to a particular area. Thinning the membrane may make the membrane more pliable, which is a desirable characteristic for the valve flaps 403. Still other post processing procedures may change the physical shape of the membranetubular structure 400, for example, by forming theloop collar 605 along the distal edge of membranetubular structure 400. Theloop collar 605 may assist in controlling the movement (translational and circumferential) of themembrane assembly 102 along the valve struts 630. Theloop collars 605 may also reduce fatigue and tear stresses in the membrane. - FIGS. 8A and 8B show an example of the result of a post processing step that forms a
loop collar 605 according to one embodiment of the present invention. To achieve this result, the membranetubular structure 400 is wrapped around at least one element of structural frame 101 (valve struts 630) and bonded to itself atbond point 800. - Another method for electro-statically spinning a tubular membrane onto a radially expandable structural frame according to another embodiment of the present invention is shown in FIG. 9. Although similar to the process described above, this alternative method provides an ESS spun membrane on the inside, as well as the outside of the structural frame. The inner and outer ESS spun membranes may mechanically adhere to each other, and in a sense encapsulated the structural frame. This configuration provides some additional features, including having a smoother interior surface that reduces turbulence, improves flow dynamics and lowers the chance of thrombosis formation.
- Similar to the embodiment described earlier, the ESS process comprises first placing a transfer sheath over a spinning mandrel as shown in
step 900. It should be noted that under certain circumstances it may not be necessary to use the transfer sheath. Such circumstances may include, for example, where the spinning mandrel is electro-statically conducting and has a surface or surface treatment that will prevent the ESS spun fiber from adhering to the mandrel. - An ESS fiber is then spun directly onto the transfer sheath creating an inner coat membrane as shown in
step 910. The ESS process should continue until an ESS tube is formed having a wall thickness of between 2 μm and 50 μm or more, and preferably, approximately 20 μm. As previously stated, the inner coat membrane covers some or all of the interior surface ofstructural frame 101. Thestructural frame 101 is then radially expanded and placed over the inner coat membrane on the spinning mandrel as shown instep 920. Expansion of thestructural frame 101 may be achieved by several different methods. One method includes taking advantage of the thermal and shape memory characteristics of particular materials. For example, shape memory materials, such as Nitinol, possess little or no recoil ability when cooled, but exhibit a high degree of memory, i.e. the ability to return to a configured shape, when heated. Cooling the Nitinolstructural frame 101 before expansion allows the structural frame to remain in the expanded configuration until being heated. Accordingly, the Nitinolstructural frame 101 can be cooled, expanded, and then placed over the inner coat membrane. Once in place, the structural frame can be heated to activate the Nitinol memory characteristics, causing the Nitinolstructural frame 101 to contract to the pre-expansion size and configuration. - The
structural frame 101 is sized such that when configured in the expanded or deployed state, it will fit tightly over the inner coat membrane on the spinning mandrel. To fit thestructural frame 101 over the inner coat membrane, thestructural frame 101 may have to be radially expanded (“super-expanded”) to a diameter slightly larger than the expanded deployed state to allow thestructural frame 101 to fit over the inner coat membrane. - Once the
structural frame 101 is placed over the inner coat membrane, another ESS fiber is spun directly onto the structural frame, as shown instep 930, to form a top-coat membrane. The ESS process should continue until the top-coat membrane tube is formed having a wall thickness of between 2 μm and 50 μm or more, and preferably, approximately 20 μm. The top-coat membrane may cover and adhere to the inner coat membrane through the interstitial spaces between the elements that comprise thestructural frame 101. - As stated in an earlier described embodiment of the invention, the
structural frame 101 is configured on the mandrel in the expanded deployed state prior to spinning the top-coat membrane. In other embodiments, it may be desirable to expand (super expand) thestructural frame 101 on the spinning mandrel during or prior to the spinning process. This procedure may alter the configuration and properties of the spun membrane, resulting in less post processing of the membrane. Post processing is described instep 960. - The
structural frame 101, with the inner coat and top coat membranes, is then removed from the spinning mandrel, as shown instep 940, and coated with a solution of highly elastic polymer as shown instep 950. As stated previously, the coating process may be achieved using several different coating methods, including spin coating, spray coating, dip coating, chemical vapor deposition, plasma coating, co-extrusion coating and insert molding. - As previously described, a representative elastomeric polymer is a fluoroelastomer. The coating process may be repeated until the desired characteristics and thickness are achieved. For a venous valve application, a thickness of between 12 μm and 100 μm, and preferably between 25 μm and 50 μm, has been found to be acceptable.
- Once the coating process is complete, some post processing of the tubular membrane may take place, as shown as an
optional step 960 in FIG. 9. - Although each of the above described ESS methods spin the fiber directly on to the structural frame, one of ordinary skill in the art would understand that a tubular membrane may also be spun separately, and then placed over the
structural frame 101 by known methods. - Another, more preferred method for forming the membrane material over and around the
structural frame 101 is shown in FIG. 10. As described earlier, this method is presented in the context of a prosthetic valve application. However, the method may be applied generally to any application where a micro-cellular foam or pourous material, particularly an ePTFE membrane, needs to be placed over and around a radially expandable structural frame. Exemplary structural frames may include stents, stents grafts, valves (including percutaneously delivered venous valves), AAA (Abdominal Aortic Aneurysm) devices, local drug delivery devices, and the like. Accordingly, the disclosed device is not meant to limit the scope of the inventive method. - In this embodiment, a tubular structure is fabricated from a polymer material that can be processed such that it exhibits an expanded cellular structure, preferably expanded Polytetrafluoroethylene (ePTFE). The ePTFE tubing is made by expanding Polytetrafluoroethylene (PTFE) tubing, under controlled conditions, as is well known in the art. This process alters the physical properties that make it satisfactory for use in medical devices. However, one of ordinary skill in the art would understand that other materials that possess the necessary characteristics could also be used.
- The method comprises first placing a transfer sheath over a mandrel as shown in
step 1000. As described earlier, the transfer sheath is a thin material that is used to prevent the tubing and coating from adhering to the mandrel. The transfer sheath may be made of sheet metal, metal foil, or polymer sheet, such as for example Polytetrafluoroethylene (PTFE) . Preferably, the transfer sheath will be made of a material that can be easily deformed, and preferably collapsed so that it can be withdrawn conveniently from the lumen of the tube once the process is complete. - The transfer sheath/mandrel combination are then coated in a solution of highly elastic polymer, such as fluoroelastomer, as shown in
step 1010, to form an inner membrane. As stated previously, the coating may be applied using various methods, including, for example, spin coating, spray coating, dip coating, chemical vapor deposition, plasma coating, co-extrusion coating and insert molding. - In one embodiment of the invention, the coating solution comprises a polymer put into solution with a solvent, such as methanol. In addition, most solvents can be used with expanded Polytetrafluoroethylene (ePTFE).
- In a preferred embodiment of the invention, the polymer comprising the coating includes Daikin's Dai-El T630, a thermoplastic elastomer based on vinylidene fluoride/hexafluoropropylene/tetrafluoroethylene (VDF/HFP/TFE) and blends thereof. Again, one of ordinary skill in the art would understand that other materials having suitable characteristics may be used for the coating, for example, other polymers, such as siliconized polyurethanes and blends thereof, including Polymer Technology Group's Pursil, Carbosil, Purspan and Purspan F.
- The coating process should continue until the inner membrane achieves a wall thickness of between 6 μm and 100 μm or more, preferably between 12 μm to 25 μm.
- In an alternate embodiment, a polymer tube, preferably an ePTFE tube, may be expanded and placed over the sheath/mandrel combination (step1015), before being contracted (step 1020). Expansion may be by any suitable expansion means known in the art, including mechanical expansion, such as by means of a balloon expansion device or expandable cage, expansion by utilizing a tapered mandrel (i.e. sliding the polymer tube over a tapered mandrel of increasing diameter) , etc. In addition other means may be used in conjunction with the expansion means to assist placing the tube over the sheath mandrel combination. These assist means may include, for example, thermally expanding the tube with heat, or chemically expanding the tube with a solvent. These methods are known in the art.
- Contraction of the tube is typically done by reversing the method used to expand the tube. For example, where the tube is naturally elastic and expanded by a mechanical expansion means, removing the expansion means would allow the tube to contract towards it pre-expansion configuration. In addition the contraction of the tube may be enhanced by applying heat or chemicals (solvents).
- Once the tube is expanded over the sheath/mandrel, the whole assembly may be coated with a solution of highly elastic polymer, such as fluoroelastomer as shown in
step 1025 to form the inner membrane. The coating process is similar to that shown instep 1010 above, and may be achieved by any method known in the art capable of achieving the desired result, including spin coating, spray coating, dip coating, chemical vapor deposition, plasma coating, co-extrusion coating and insert molding. - The coating process described in
step 1025 should continue until the inner membrane described in the alternate embodiment is coated with a polymer base having a wall thickness of between 6 μm and 100 μm or more, preferably between 12 μm to 25 μm. - The
structural frame 101 is then radially expanded and positioned over the inner membrane as shown instep 1030. Thestructural frame 101 may be radially expanded using any know expansion means, including a balloon expansion device or frame expansion device. In one embodiment of the invention, thestructural frame 101 is constructed from a shape memory alloy, such as Nitinol. As previously described, Nitinol characteristically holds a deformed shaped when cooled, and returns to its original shape when heated. Accordingly, it is possible to hold a Nitinolstructural frame 101 in the radially expanded state by cooling the frame before the expansion means is removed. This will facilitate placement of the Nitinol structural frame over the inner membrane. - The
structural frame 101 may then be radially contracted over the inner membrane, as shown instep 1040. It is desirable to maintain a slight interference fit between thestructural frame 101 and the inner membrane. The method to radially contract thestructural frame 101 may depend on the material and type of construction of thestructural frame 101, and is not meant to limit the scope of the invention. As described above, astructural frame 101 constructed from a shape memory alloy, such as Nitinol, can be radially contracted (to the pre-expanded and cooled size) by heating. Depending on the material used, other methods that may also be employed to radially contract the structural frame include, simply removing the expansion means providing the radial expansion force, or applying a compressive force about thestructural frame 101. Still other methods to radially contract thestructural frame 101 would be obvious to one of skill in the art. - Once the
structural frame 101 is contracted over the inner membrane, a second polymer tube, preferably an ePTFE tube, is expanded and placed over the structural frame, as shown instep 1050, forming an outer membrane. The tube is then contracted into position as shown instep 1060. As described earlier, the tube may be expanded by several different means, including mechanical, thermal, or chemical (solvents) expansion. Similarly, contraction of the tube may be accomplished by the methods described instep 1020. - In embodiments where two separate ePTFE tubes are used for the inner and outer membranes, as described in
steps alternate steps 1015 through 1025), the tube should have a wall thickness before expansion of between 50 μm and 100 μm; yielding a wall thickness after expansion of between 12 μm and 20 μm. - The inner and outer membranes combine to form a membrane structure. In the valve example described above, the membrane structure would represent membrane
tubular structure 400, while the structural frame would represent thestructural frame 101. - Once the membrane structure is formed, some or all of the assembly may be optionally coated with a solution of a highly elastic polymer, such as a elastomeric polymer, as shown in
step 1070. The coating may be applied by any method known in the art, including spin coating, spray coating, dip coating, chemical vapor deposition, plasma coating, co-extrusion coating and insert molding. - As described earlier (see step1010) the coating solution may be a fluoroelastomer. In one embodiment of the invention, the coating is Daikin G701BP, which is a 60/40% VDF/HFP. Again, one of ordinary skill in the art would understand that other materials having suitable characteristics might be used for the coating, for example, other polymers, such as siliconized polyurethane.
- The coating process should continue until the coating achieves a wall thickness of between 6 μm and 100 μm or more, preferably between 12 μm to 25 μm.
- Once the coating process is complete, some post processing of the membrane structure may take place to achieve particular desired characteristics or configurations. This post processing step is shown as
optional step 1080 in FIG. 10. - By way of example, for valve applications, the
post processing step 1080 may be used to form or shape valve cusps, similar tocusps 404, or valve flaps, such asflaps 403, in the membrane structure. In addition, post processing may change the characteristics of the membrane structure by thickening or thinning the membrane in particular locations. Thickening the membrane may add rigidity and reinforcement to a particular area. Thinning the membrane may make the membrane more pliable. Still other post processing procedures may change the physical shape of the membrane structure, for example, by forming theloop collar 605 along the distal edge ofmembrane assembly 102. Theloop collar 605 may assist in controlling the translational and circumferential movement of themembrane assembly 102 along the valve struts 630. Theloop collars 605 may also reduce fatigue and tear stresses in the membrane. - It is important to note that the local delivery of drug/drug combinations may be utilized to treat a wide variety of conditions utilizing any number of medical devices, or to enhance the function and/or life of the device. Medical devices that may benefit from this treatment include, for example, the frame based unidirectional flow prosthetic implant subject of the present invention.
- Accordingly, in addition to the embodiments described above, therapeutic or pharmaceutic agents may be added to any component of the device during fabrication, including, for example, the ESS fiber, polymer or coating solution, membrane tube, structural frame or inner and outer membrane, to treat any number of conditions. In addition, therapeutic or pharmaceutic agents may be applied to the device, such as in the form of a drug or drug eluting layer, or surface treatment after the device has been formed. In a preferred embodiment, the therapeutic and pharmaceutic agents may include any one or more of the following: antiproliferative/antimitotic agents including natural products such as vinca alkaloids (i.e. vinblastine, vincristine, and vinorelbine), paclitaxel, epidipodophyllotoxins (i.e. etoposide, teniposide), antibiotics (dactinomycin (actinomycin D) daunorubicin, doxorubicin and idarubicin) anthracyclines, mitoxantrone, bleomycins, plicamycin (mithramycin) and mitomycin, enzymes (L-asparaginase which systemically metabolizes L-asparagine and deprives cells which do not have the capacity to synthesize their own asparagine); antiplatelet agents such as G(GP) llb/llla inhibitors and vitronectin receptor antagonists; antiproliferative/antimitotic alkylating agents such as nitrogen mustards (mechlorethamine, cyclophosphamide and analogs, melphalan, chlorambucil), ethylenimines and methylmelamines (hexamethylmelamine and thiotepa), alkyl sulfonates-busulfan, nirtosoureas (carmustine (BCNU) and analogs, streptozocin) , trazenes-dacarbazinine (DTIC); antiproliferative/antimitotic antimetabolites such as folic acid analogs (methotrexate), pyrimidine analogs (fluorouracil, floxuridine, and cytarabine), purine analogs and related inhibitors (mercaptopurine, thioguanine, pentostatin and 2-chlorodeoxyadenosine {cladribine}); platinum coordination complexes (cisplatin, carboplatin), procarbazine, hydroxyurea, mitotane, aminoglutethimide; hormones (i.e. estrogen); anticoagulants (heparin, synthetic heparin salts and other inhibitors of thrombin); fibrinolytic agents (such as tissue plasminogen activator, streptokinase and urokinase), aspirin, dipyridamole, ticlopidine, clopidogrel, abciximab; antimigratory; antisecretory (breveldin); anti-inflammatory: such as adrenocortical steroids (cortisol, cortisone, fludrocortisone, prednisone, prednisolone, 6α-methylprednisolone, triamcinolone, betamethasone, and dexamethasone), non-steroidal agents (salicylic acid derivatives i.e. aspirin; para-aminophenol derivatives i.e. acetominophen; indole and indene acetic acids (indomethacin, sulindac, and etodalac), heteroaryl acetic acids (tolmetin, diclofenac, and ketorolac), arylpropionic acids (ibuprofen and derivatives), anthranilic acids (mefenamic acid, and meclofenamic acid), enolic acids (piroxicam, tenoxicam, phenylbutazone, and oxyphenthatrazone) , nabumetone, gold compounds (auranofin, aurothioglucose, gold sodium thiomalate); immunosuppressives: (cyclosporine, tacrolimus (FK-506), sirolimus (rapamycin), azathioprine, mycophenolate mofetil); angiogenic agents: vascular endothelial growth factor (VEGF), fibroblast growth factor (FGF); angiotensin receptor blockers; nitric oxide donors; anti-sense oligionucleotides and combinations thereof; cell cycle inhibitors, mTOR inhibitors, and growth factor receptor signal transduction kinase inhibitors; retenoids; cyclin/CDK inhibitors; HMG co-enzyme reductase inhibitors (statins); and protease inhibitors.
- While a number of variations of the invention have been shown and described in detail, other modifications and methods of use contemplated within the scope of this invention will be readily apparent to those of skill in the art based upon this disclosure. It is contemplated that various combinations or subcombinations of the specific embodiments may be made and still fall within the scope of the invention. For example, the embodiments variously shown to be prosthetic “venous valves” may be modified to instead incorporate prosthetic “heart valves” and are also contemplated. Moreover, all assemblies described are believed useful when modified to treat other vessels or lumens in the body, in particular other regions of the body where fluid flow in a body vessel or lumen needs to be controlled or regulated. This may include, for example, the coronary, vascular, non-vascular and peripheral vessels and ducts. Accordingly, it should be understood that various applications, modifications and substitutions may be made of equivalents without departing from the spirit of the invention or the scope of the following claims.
- The following claims are provided to illustrate examples of some beneficial aspects of the subject matter disclosed herein which are within the scope of the present invention.
Claims (7)
1. A prosthetic valve comprising:
a radially expandable structural frame having a plurality of distal crowns, the structural frame being formed from a lattice of interconnected elements, and having a substantially cylindrical configuration with first and second open ends and a longitudinal axis extending there between;
a tubular biocompatible membrane coaxially disposed over at least a portion of the structural frame such that the structural frame supports the biocompatible membrane assembly in a slack condition between the distal crowns.
2. The prosthetic valve of claim 1 wherein the structural frame further comprises a valve strut attached to at least one of the distal crowns and extending in a distal direction substantially parallel to the longitudinal axis.
3. The prosthetic valve of claim 1 wherein the distal crowns are articulating.
4. The prosthetic valve of claim 1 wherein the biocompatible membrane assembly extends in a distal direction past the distal crowns.
5. A prosthetic valve comprising:
a radially expandable structural frame having a plurality of distal crowns, the structural frame being formed from a lattice of interconnected elements, and having a substantially cylindrical configuration with first and second open ends and a longitudinal axis extending there between;
a tubular biocompatible membrane coaxially disposed over at least a portion of the structural frame such that the structural frame supports the biocompatible membrane assembly in a flexible condition between the distal crowns.
6. A prosthetic valve comprising:
a substantially cylindrical structural frame having a hoop structure, the hoop structure having a plurality of distal crowns;
a substantially cylindrical biocompatible membrane assembly coaxially disposed over the structural frame such that the structural frame supports the biocompatible membrane assembly in a slack condition between the distal crowns.
7. A prosthetic valve having a radially expandable structural frame comprising:
a cylindrical hoop structure having a plurality of distal and proximal crowns;
a proximal anchor formed from a lattice of interconnected elements and having a substantially cylindrical configurations;
one or more connecting members, the one or more connecting members having a first and a second end, the first end of each connecting member being attached to the proximal anchor and the second end of each connecting member being attached to the hoop structure; and
a substantially cylindrical biocompatible membrane assembly attached to the proximal anchor and extending distally along the one or more connecting members to the distal crowns, such that the distal crowns.
Priority Applications (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US10/431,967 US20030236568A1 (en) | 2002-05-10 | 2003-05-08 | Multi-lobed frame based unidirectional flow prosthetic implant |
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US37960402P | 2002-05-10 | 2002-05-10 | |
US10/431,967 US20030236568A1 (en) | 2002-05-10 | 2003-05-08 | Multi-lobed frame based unidirectional flow prosthetic implant |
Publications (1)
Publication Number | Publication Date |
---|---|
US20030236568A1 true US20030236568A1 (en) | 2003-12-25 |
Family
ID=29420545
Family Applications (3)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US10/430,113 Abandoned US20030225447A1 (en) | 2002-05-10 | 2003-05-06 | Method of making a medical device having a thin wall tubular membrane over a structural frame |
US10/431,967 Abandoned US20030236568A1 (en) | 2002-05-10 | 2003-05-08 | Multi-lobed frame based unidirectional flow prosthetic implant |
US10/434,891 Active 2025-07-09 US7758632B2 (en) | 2002-05-10 | 2003-05-09 | Frame based unidirectional flow prosthetic implant |
Family Applications Before (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US10/430,113 Abandoned US20030225447A1 (en) | 2002-05-10 | 2003-05-06 | Method of making a medical device having a thin wall tubular membrane over a structural frame |
Family Applications After (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US10/434,891 Active 2025-07-09 US7758632B2 (en) | 2002-05-10 | 2003-05-09 | Frame based unidirectional flow prosthetic implant |
Country Status (9)
Country | Link |
---|---|
US (3) | US20030225447A1 (en) |
EP (4) | EP2149350A3 (en) |
JP (2) | JP2005525169A (en) |
AT (1) | ATE470406T1 (en) |
AU (5) | AU2003225291A1 (en) |
CA (3) | CA2485285A1 (en) |
DE (1) | DE60332938D1 (en) |
MX (3) | MXPA04011144A (en) |
WO (3) | WO2003094795A1 (en) |
Cited By (153)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20040098112A1 (en) * | 1999-10-21 | 2004-05-20 | Scimed Life Systems, Inc. | Implantable prosthetic valve |
US20040225348A1 (en) * | 2003-04-08 | 2004-11-11 | Case Brian C. | Intraluminal support device with graft |
US20050143807A1 (en) * | 2000-02-03 | 2005-06-30 | Dusan Pavcnik | Implantable vascular device comprising a bioabsorbable frame |
US6945957B2 (en) | 2002-12-30 | 2005-09-20 | Scimed Life Systems, Inc. | Valve treatment catheter and methods |
US7007698B2 (en) | 2002-04-03 | 2006-03-07 | Boston Scientific Corporation | Body lumen closure |
WO2006031469A1 (en) * | 2004-09-02 | 2006-03-23 | Boston Scientific Limited | Cardiac valve, system, and method |
US20060173532A1 (en) * | 2004-12-20 | 2006-08-03 | Jacob Flagle | Intraluminal support frame and medical devices including the support frame |
US20060212110A1 (en) * | 2003-03-17 | 2006-09-21 | Osborne Thomas A | Vascular valve with removable support component |
WO2006113496A2 (en) * | 2005-04-15 | 2006-10-26 | Boston Scientific Limited | Valve apparatus, system and method |
US20060259134A1 (en) * | 2003-07-08 | 2006-11-16 | Ehud Schwammenthal | Implantable prosthetic devices particularly for transarterial delivery in the treatment of aortic stenosis, and methods of implanting such devices |
US20060259137A1 (en) * | 2003-10-06 | 2006-11-16 | Jason Artof | Minimally invasive valve replacement system |
WO2006123340A3 (en) * | 2005-05-17 | 2007-03-29 | Nicast Ltd | Electrically charged implantable medical device |
US20070185565A1 (en) * | 2003-07-08 | 2007-08-09 | Ventor Technologies Ltd. | Fluid flow prosthetic device |
US20070260327A1 (en) * | 2003-04-24 | 2007-11-08 | Case Brian C | Artificial Valve Prosthesis with Improved Flow Dynamics |
US20070288087A1 (en) * | 2006-05-30 | 2007-12-13 | Cook Incorporated | Artificial valve prosthesis |
US20080039952A1 (en) * | 2006-08-09 | 2008-02-14 | Coherex Medical, Inc. | Devices for reducing the size of an internal tissue opening |
US20080071361A1 (en) * | 2006-09-19 | 2008-03-20 | Yosi Tuval | Leaflet-sensitive valve fixation member |
US20090012596A1 (en) * | 2007-07-06 | 2009-01-08 | Boston Scientific Scimed, Inc. | Stent with Bioabsorbable Membrane |
US20090240320A1 (en) * | 2008-03-18 | 2009-09-24 | Yosi Tuval | Valve suturing and implantation procedures |
US20100010518A1 (en) * | 2008-07-09 | 2010-01-14 | Joshua Stopek | Anastomosis Sheath And Method Of Use |
WO2010006627A1 (en) | 2008-07-17 | 2010-01-21 | Nvt Ag | Cardiac valve prosthesis system |
US7658759B2 (en) * | 2003-04-24 | 2010-02-09 | Cook Incorporated | Intralumenally implantable frames |
US7670368B2 (en) | 2005-02-07 | 2010-03-02 | Boston Scientific Scimed, Inc. | Venous valve apparatus, system, and method |
US7682385B2 (en) | 2002-04-03 | 2010-03-23 | Boston Scientific Corporation | Artificial valve |
US7708775B2 (en) | 2005-05-24 | 2010-05-04 | Edwards Lifesciences Corporation | Methods for rapid deployment of prosthetic heart valves |
US20100114296A1 (en) * | 2003-04-24 | 2010-05-06 | Cook Incorporated | Intralumenally-implantable frames |
US20100114300A1 (en) * | 2004-12-01 | 2010-05-06 | Cook Incorporated | Medical device with leak path |
US7776053B2 (en) | 2000-10-26 | 2010-08-17 | Boston Scientific Scimed, Inc. | Implantable valve system |
US7780722B2 (en) | 2005-02-07 | 2010-08-24 | Boston Scientific Scimed, Inc. | Venous valve apparatus, system, and method |
US7799038B2 (en) | 2006-01-20 | 2010-09-21 | Boston Scientific Scimed, Inc. | Translumenal apparatus, system, and method |
US7819915B2 (en) | 2000-07-27 | 2010-10-26 | Edwards Lifesciences Corporation | Heart valve holders and handling clips therefor |
US7846199B2 (en) | 2007-11-19 | 2010-12-07 | Cook Incorporated | Remodelable prosthetic valve |
US7854755B2 (en) | 2005-02-01 | 2010-12-21 | Boston Scientific Scimed, Inc. | Vascular catheter, system, and method |
US7854761B2 (en) | 2003-12-19 | 2010-12-21 | Boston Scientific Scimed, Inc. | Methods for venous valve replacement with a catheter |
DE102009037739A1 (en) * | 2009-06-29 | 2010-12-30 | Be Innovative Gmbh | Percutaneously implantable valve stent, device for its application and method for producing the valve stent |
US7867274B2 (en) | 2005-02-23 | 2011-01-11 | Boston Scientific Scimed, Inc. | Valve apparatus, system and method |
US7878966B2 (en) | 2005-02-04 | 2011-02-01 | Boston Scientific Scimed, Inc. | Ventricular assist and support device |
US7892276B2 (en) | 2007-12-21 | 2011-02-22 | Boston Scientific Scimed, Inc. | Valve with delayed leaflet deployment |
US7951197B2 (en) | 2005-04-08 | 2011-05-31 | Medtronic, Inc. | Two-piece prosthetic valves with snap-in connection and methods for use |
US7951189B2 (en) | 2005-09-21 | 2011-05-31 | Boston Scientific Scimed, Inc. | Venous valve, system, and method with sinus pocket |
US7959674B2 (en) | 2002-07-16 | 2011-06-14 | Medtronic, Inc. | Suture locking assembly and method of use |
US7967853B2 (en) | 2007-02-05 | 2011-06-28 | Boston Scientific Scimed, Inc. | Percutaneous valve, system and method |
US7967857B2 (en) | 2006-01-27 | 2011-06-28 | Medtronic, Inc. | Gasket with spring collar for prosthetic heart valves and methods for making and using them |
US7972377B2 (en) | 2001-12-27 | 2011-07-05 | Medtronic, Inc. | Bioprosthetic heart valve |
US7981153B2 (en) | 2002-12-20 | 2011-07-19 | Medtronic, Inc. | Biologically implantable prosthesis methods of using |
US8012198B2 (en) | 2005-06-10 | 2011-09-06 | Boston Scientific Scimed, Inc. | Venous valve, system, and method |
US8021421B2 (en) | 2003-08-22 | 2011-09-20 | Medtronic, Inc. | Prosthesis heart valve fixturing device |
US8021161B2 (en) | 2006-05-01 | 2011-09-20 | Edwards Lifesciences Corporation | Simulated heart valve root for training and testing |
US8038708B2 (en) | 2001-02-05 | 2011-10-18 | Cook Medical Technologies Llc | Implantable device with remodelable material and covering material |
US20110301692A1 (en) * | 2001-07-04 | 2011-12-08 | Medtronic Corevalve Llc | Assembly for Placing a Prosthetic Valve in a Duct in the Body |
US8128681B2 (en) | 2003-12-19 | 2012-03-06 | Boston Scientific Scimed, Inc. | Venous valve apparatus, system, and method |
US8133270B2 (en) | 2007-01-08 | 2012-03-13 | California Institute Of Technology | In-situ formation of a valve |
US8211169B2 (en) | 2005-05-27 | 2012-07-03 | Medtronic, Inc. | Gasket with collar for prosthetic heart valves and methods for using them |
US8216299B2 (en) | 2004-04-01 | 2012-07-10 | Cook Medical Technologies Llc | Method to retract a body vessel wall with remodelable material |
US8308798B2 (en) | 2008-12-19 | 2012-11-13 | Edwards Lifesciences Corporation | Quick-connect prosthetic heart valve and methods |
US8337545B2 (en) | 2004-02-09 | 2012-12-25 | Cook Medical Technologies Llc | Woven implantable device |
US8348998B2 (en) | 2009-06-26 | 2013-01-08 | Edwards Lifesciences Corporation | Unitary quick connect prosthetic heart valve and deployment system and methods |
US8449625B2 (en) | 2009-10-27 | 2013-05-28 | Edwards Lifesciences Corporation | Methods of measuring heart valve annuluses for valve replacement |
US8475525B2 (en) | 2010-01-22 | 2013-07-02 | 4Tech Inc. | Tricuspid valve repair using tension |
US8506625B2 (en) | 2005-07-13 | 2013-08-13 | Edwards Lifesciences Corporation | Contoured sewing ring for a prosthetic mitral heart valve |
US20130226291A1 (en) * | 1999-06-02 | 2013-08-29 | Dusan Pavcnik | Implantable vascular device |
US8574257B2 (en) | 2005-02-10 | 2013-11-05 | Edwards Lifesciences Corporation | System, device, and method for providing access in a cardiovascular environment |
US8603161B2 (en) | 2003-10-08 | 2013-12-10 | Medtronic, Inc. | Attachment device and methods of using the same |
US8641757B2 (en) | 2010-09-10 | 2014-02-04 | Edwards Lifesciences Corporation | Systems for rapidly deploying surgical heart valves |
US8652204B2 (en) | 2010-04-01 | 2014-02-18 | Medtronic, Inc. | Transcatheter valve with torsion spring fixation and related systems and methods |
US8821569B2 (en) | 2006-04-29 | 2014-09-02 | Medtronic, Inc. | Multiple component prosthetic heart valve assemblies and methods for delivering them |
US8828079B2 (en) | 2007-07-26 | 2014-09-09 | Boston Scientific Scimed, Inc. | Circulatory valve, system and method |
US8834564B2 (en) | 2006-09-19 | 2014-09-16 | Medtronic, Inc. | Sinus-engaging valve fixation member |
US8845720B2 (en) | 2010-09-27 | 2014-09-30 | Edwards Lifesciences Corporation | Prosthetic heart valve frame with flexible commissures |
US8961596B2 (en) | 2010-01-22 | 2015-02-24 | 4Tech Inc. | Method and apparatus for tricuspid valve repair using tension |
US8961594B2 (en) | 2012-05-31 | 2015-02-24 | 4Tech Inc. | Heart valve repair system |
US8986374B2 (en) | 2010-05-10 | 2015-03-24 | Edwards Lifesciences Corporation | Prosthetic heart valve |
USD732666S1 (en) | 2005-05-13 | 2015-06-23 | Medtronic Corevalve, Inc. | Heart valve prosthesis |
US9078747B2 (en) | 2011-12-21 | 2015-07-14 | Edwards Lifesciences Corporation | Anchoring device for replacing or repairing a heart valve |
US9125741B2 (en) | 2010-09-10 | 2015-09-08 | Edwards Lifesciences Corporation | Systems and methods for ensuring safe and rapid deployment of prosthetic heart valves |
US9155617B2 (en) | 2004-01-23 | 2015-10-13 | Edwards Lifesciences Corporation | Prosthetic mitral valve |
US9241702B2 (en) | 2010-01-22 | 2016-01-26 | 4Tech Inc. | Method and apparatus for tricuspid valve repair using tension |
US9248016B2 (en) | 2009-03-31 | 2016-02-02 | Edwards Lifesciences Corporation | Prosthetic heart valve system |
US9308360B2 (en) | 2007-08-23 | 2016-04-12 | Direct Flow Medical, Inc. | Translumenally implantable heart valve with formed in place support |
US9307980B2 (en) | 2010-01-22 | 2016-04-12 | 4Tech Inc. | Tricuspid valve repair using tension |
US9314334B2 (en) | 2008-11-25 | 2016-04-19 | Edwards Lifesciences Corporation | Conformal expansion of prosthetic devices to anatomical shapes |
CN105496607A (en) * | 2016-01-11 | 2016-04-20 | 北京迈迪顶峰医疗科技有限公司 | Aortic valve device conveyed by catheter |
US9370418B2 (en) | 2010-09-10 | 2016-06-21 | Edwards Lifesciences Corporation | Rapidly deployable surgical heart valves |
US9393110B2 (en) | 2010-10-05 | 2016-07-19 | Edwards Lifesciences Corporation | Prosthetic heart valve |
US9439762B2 (en) | 2000-06-01 | 2016-09-13 | Edwards Lifesciences Corporation | Methods of implant of a heart valve with a convertible sewing ring |
US9445897B2 (en) | 2012-05-01 | 2016-09-20 | Direct Flow Medical, Inc. | Prosthetic implant delivery device with introducer catheter |
US9468527B2 (en) | 2013-06-12 | 2016-10-18 | Edwards Lifesciences Corporation | Cardiac implant with integrated suture fasteners |
US9504566B2 (en) | 2014-06-20 | 2016-11-29 | Edwards Lifesciences Corporation | Surgical heart valves identifiable post-implant |
US9549816B2 (en) | 2014-04-03 | 2017-01-24 | Edwards Lifesciences Corporation | Method for manufacturing high durability heart valve |
US9554901B2 (en) | 2010-05-12 | 2017-01-31 | Edwards Lifesciences Corporation | Low gradient prosthetic heart valve |
US9579194B2 (en) | 2003-10-06 | 2017-02-28 | Medtronic ATS Medical, Inc. | Anchoring structure with concave landing zone |
US9585752B2 (en) | 2014-04-30 | 2017-03-07 | Edwards Lifesciences Corporation | Holder and deployment system for surgical heart valves |
US9603708B2 (en) | 2010-05-19 | 2017-03-28 | Dfm, Llc | Low crossing profile delivery catheter for cardiovascular prosthetic implant |
US9622859B2 (en) | 2005-02-01 | 2017-04-18 | Boston Scientific Scimed, Inc. | Filter system and method |
US9636221B2 (en) | 2007-09-26 | 2017-05-02 | St. Jude Medical, Inc. | Collapsible prosthetic heart valves |
US9668859B2 (en) | 2011-08-05 | 2017-06-06 | California Institute Of Technology | Percutaneous heart valve delivery systems |
US20170156863A1 (en) * | 2015-12-03 | 2017-06-08 | Medtronic Vascular, Inc. | Venous valve prostheses |
US9675449B2 (en) | 2008-07-15 | 2017-06-13 | St. Jude Medical, Llc | Collapsible and re-expandable prosthetic heart valve cuff designs and complementary technological applications |
US20170172771A1 (en) * | 2014-07-20 | 2017-06-22 | Elchanan Bruckheimer | Pulmonary artery implant apparatus and methods of use thereof |
US9693865B2 (en) | 2013-01-09 | 2017-07-04 | 4 Tech Inc. | Soft tissue depth-finding tool |
US9744037B2 (en) | 2013-03-15 | 2017-08-29 | California Institute Of Technology | Handle mechanism and functionality for repositioning and retrieval of transcatheter heart valves |
CN107260367A (en) * | 2009-11-02 | 2017-10-20 | 西美蒂斯股份公司 | Sustainer bioprosthesis and the system for its delivering |
US9801720B2 (en) | 2014-06-19 | 2017-10-31 | 4Tech Inc. | Cardiac tissue cinching |
US9820851B2 (en) | 2007-09-28 | 2017-11-21 | St. Jude Medical, Llc | Collapsible-expandable prosthetic heart valves with structures for clamping native tissue |
US9907547B2 (en) | 2014-12-02 | 2018-03-06 | 4Tech Inc. | Off-center tissue anchors |
US9907681B2 (en) | 2013-03-14 | 2018-03-06 | 4Tech Inc. | Stent with tether interface |
US9913715B2 (en) | 2013-11-06 | 2018-03-13 | St. Jude Medical, Cardiology Division, Inc. | Paravalvular leak sealing mechanism |
US9919137B2 (en) | 2013-08-28 | 2018-03-20 | Edwards Lifesciences Corporation | Integrated balloon catheter inflation system |
US9956384B2 (en) | 2014-01-24 | 2018-05-01 | Cook Medical Technologies Llc | Articulating balloon catheter and method for using the same |
US10022114B2 (en) | 2013-10-30 | 2018-07-17 | 4Tech Inc. | Percutaneous tether locking |
US10039643B2 (en) | 2013-10-30 | 2018-08-07 | 4Tech Inc. | Multiple anchoring-point tension system |
US10052095B2 (en) | 2013-10-30 | 2018-08-21 | 4Tech Inc. | Multiple anchoring-point tension system |
US10058425B2 (en) | 2013-03-15 | 2018-08-28 | Edwards Lifesciences Corporation | Methods of assembling a valved aortic conduit |
US10058323B2 (en) | 2010-01-22 | 2018-08-28 | 4 Tech Inc. | Tricuspid valve repair using tension |
US10080653B2 (en) | 2015-09-10 | 2018-09-25 | Edwards Lifesciences Corporation | Limited expansion heart valve |
USD846122S1 (en) | 2016-12-16 | 2019-04-16 | Edwards Lifesciences Corporation | Heart valve sizer |
US10441415B2 (en) | 2013-09-20 | 2019-10-15 | Edwards Lifesciences Corporation | Heart valves with increased effective orifice area |
US10456245B2 (en) | 2016-05-16 | 2019-10-29 | Edwards Lifesciences Corporation | System and method for applying material to a stent |
US10456246B2 (en) | 2015-07-02 | 2019-10-29 | Edwards Lifesciences Corporation | Integrated hybrid heart valves |
US10463485B2 (en) | 2017-04-06 | 2019-11-05 | Edwards Lifesciences Corporation | Prosthetic valve holders with automatic deploying mechanisms |
USD867594S1 (en) | 2015-06-19 | 2019-11-19 | Edwards Lifesciences Corporation | Prosthetic heart valve |
US20190351099A1 (en) * | 2018-05-21 | 2019-11-21 | Aran Biomedical Teoranta | Insertable medical devices with low profile composite coverings |
US10543080B2 (en) | 2011-05-20 | 2020-01-28 | Edwards Lifesciences Corporation | Methods of making encapsulated heart valves |
US10667904B2 (en) | 2016-03-08 | 2020-06-02 | Edwards Lifesciences Corporation | Valve implant with integrated sensor and transmitter |
US10695170B2 (en) | 2015-07-02 | 2020-06-30 | Edwards Lifesciences Corporation | Hybrid heart valves adapted for post-implant expansion |
US10722316B2 (en) | 2013-11-06 | 2020-07-28 | Edwards Lifesciences Corporation | Bioprosthetic heart valves having adaptive seals to minimize paravalvular leakage |
US10799353B2 (en) | 2017-04-28 | 2020-10-13 | Edwards Lifesciences Corporation | Prosthetic heart valve with collapsible holder |
US10806579B2 (en) | 2017-10-20 | 2020-10-20 | Boston Scientific Scimed, Inc. | Heart valve repair implant for treating tricuspid regurgitation |
EP3528748B1 (en) | 2016-10-24 | 2021-01-20 | Nvt Ag | Intraluminal vessel prosthesis for implantation into the heart or cardiac vessels of a patient |
USD908874S1 (en) | 2018-07-11 | 2021-01-26 | Edwards Lifesciences Corporation | Collapsible heart valve sizer |
US10940167B2 (en) | 2012-02-10 | 2021-03-09 | Cvdevices, Llc | Methods and uses of biological tissues for various stent and other medical applications |
US10993805B2 (en) | 2008-02-26 | 2021-05-04 | Jenavalve Technology, Inc. | Stent for the positioning and anchoring of a valvular prosthesis in an implantation site in the heart of a patient |
US11007058B2 (en) | 2013-03-15 | 2021-05-18 | Edwards Lifesciences Corporation | Valved aortic conduits |
US11065138B2 (en) | 2016-05-13 | 2021-07-20 | Jenavalve Technology, Inc. | Heart valve prosthesis delivery system and method for delivery of heart valve prosthesis with introducer sheath and loading system |
US11135057B2 (en) | 2017-06-21 | 2021-10-05 | Edwards Lifesciences Corporation | Dual-wireform limited expansion heart valves |
US11185405B2 (en) | 2013-08-30 | 2021-11-30 | Jenavalve Technology, Inc. | Radially collapsible frame for a prosthetic valve and method for manufacturing such a frame |
US11197754B2 (en) | 2017-01-27 | 2021-12-14 | Jenavalve Technology, Inc. | Heart valve mimicry |
US11259919B2 (en) | 2008-01-24 | 2022-03-01 | Medtronic, Inc. | Stents for prosthetic heart valves |
US11284999B2 (en) | 2008-01-24 | 2022-03-29 | Medtronic, Inc. | Stents for prosthetic heart valves |
US20220096225A1 (en) * | 2007-06-04 | 2022-03-31 | St. Jude Medical, Llc | Prosthetic Heart Valves |
US11304801B2 (en) | 2006-09-19 | 2022-04-19 | Medtronic Ventor Technologies Ltd. | Sinus-engaging valve fixation member |
US11337800B2 (en) | 2015-05-01 | 2022-05-24 | Jenavalve Technology, Inc. | Device and method with reduced pacemaker rate in heart valve replacement |
US11337805B2 (en) | 2018-01-23 | 2022-05-24 | Edwards Lifesciences Corporation | Prosthetic valve holders, systems, and methods |
US11357624B2 (en) | 2007-04-13 | 2022-06-14 | Jenavalve Technology, Inc. | Medical device for treating a heart valve insufficiency |
US11364132B2 (en) | 2017-06-05 | 2022-06-21 | Restore Medical Ltd. | Double walled fixed length stent like apparatus and methods of use thereof |
US11406495B2 (en) | 2013-02-11 | 2022-08-09 | Cook Medical Technologies Llc | Expandable support frame and medical device |
US11517431B2 (en) | 2005-01-20 | 2022-12-06 | Jenavalve Technology, Inc. | Catheter system for implantation of prosthetic heart valves |
US11554012B2 (en) | 2019-12-16 | 2023-01-17 | Edwards Lifesciences Corporation | Valve holder assembly with suture looping protection |
US11564794B2 (en) | 2008-02-26 | 2023-01-31 | Jenavalve Technology, Inc. | Stent for the positioning and anchoring of a valvular prosthesis in an implantation site in the heart of a patient |
US11589981B2 (en) | 2010-05-25 | 2023-02-28 | Jenavalve Technology, Inc. | Prosthetic heart valve and transcatheter delivered endoprosthesis comprising a prosthetic heart valve and a stent |
US11690709B2 (en) | 2015-09-02 | 2023-07-04 | Edwards Lifesciences Corporation | Methods for securing a transcatheter valve to a bioprosthetic cardiac structure |
US11771434B2 (en) | 2016-09-28 | 2023-10-03 | Restore Medical Ltd. | Artery medical apparatus and methods of use thereof |
US11857417B2 (en) | 2020-08-16 | 2024-01-02 | Trilio Medical Ltd. | Leaflet support |
Families Citing this family (322)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US6006134A (en) * | 1998-04-30 | 1999-12-21 | Medtronic, Inc. | Method and device for electronically controlling the beating of a heart using venous electrical stimulation of nerve fibers |
US6395019B2 (en) | 1998-02-09 | 2002-05-28 | Trivascular, Inc. | Endovascular graft |
US20070043435A1 (en) * | 1999-11-17 | 2007-02-22 | Jacques Seguin | Non-cylindrical prosthetic valve system for transluminal delivery |
US8016877B2 (en) * | 1999-11-17 | 2011-09-13 | Medtronic Corevalve Llc | Prosthetic valve for transluminal delivery |
US7018406B2 (en) | 1999-11-17 | 2006-03-28 | Corevalve Sa | Prosthetic valve for transluminal delivery |
US8579966B2 (en) | 1999-11-17 | 2013-11-12 | Medtronic Corevalve Llc | Prosthetic valve for transluminal delivery |
US7749245B2 (en) | 2000-01-27 | 2010-07-06 | Medtronic, Inc. | Cardiac valve procedure methods and devices |
US6692513B2 (en) * | 2000-06-30 | 2004-02-17 | Viacor, Inc. | Intravascular filter with debris entrapment mechanism |
US20050267560A1 (en) * | 2000-02-03 | 2005-12-01 | Cook Incorporated | Implantable bioabsorbable valve support frame |
AU2001271667A1 (en) * | 2000-06-30 | 2002-01-14 | Viacor Incorporated | Method and apparatus for performing a procedure on a cardiac valve |
JP2004506469A (en) | 2000-08-18 | 2004-03-04 | アトリテック, インコーポレイテッド | Expandable implantable device for filtering blood flow from the atrial appendage |
US8623077B2 (en) | 2001-06-29 | 2014-01-07 | Medtronic, Inc. | Apparatus for replacing a cardiac valve |
US8771302B2 (en) * | 2001-06-29 | 2014-07-08 | Medtronic, Inc. | Method and apparatus for resecting and replacing an aortic valve |
US7544206B2 (en) | 2001-06-29 | 2009-06-09 | Medtronic, Inc. | Method and apparatus for resecting and replacing an aortic valve |
US7097659B2 (en) | 2001-09-07 | 2006-08-29 | Medtronic, Inc. | Fixation band for affixing a prosthetic heart valve to tissue |
US7090693B1 (en) | 2001-12-20 | 2006-08-15 | Boston Scientific Santa Rosa Corp. | Endovascular graft joint and method for manufacture |
US8308797B2 (en) | 2002-01-04 | 2012-11-13 | Colibri Heart Valve, LLC | Percutaneously implantable replacement heart valve device and method of making same |
AU2003263454A1 (en) * | 2002-09-19 | 2004-04-08 | Petrus Besselink | Vascular filter with improved strength and flexibility |
CO5500017A1 (en) * | 2002-09-23 | 2005-03-31 | 3F Therapeutics Inc | MITRAL PROTESTIC VALVE |
AU2003285943B2 (en) * | 2002-10-24 | 2008-08-21 | Boston Scientific Limited | Venous valve apparatus and method |
FR2847150B1 (en) * | 2002-11-15 | 2005-01-21 | Claude Mialhe | OCCLUSIVE DEVICE WITH MEDICAL OR SURGICAL DESTINATION |
US6945992B2 (en) * | 2003-04-22 | 2005-09-20 | Medtronic Vascular, Inc. | Single-piece crown stent |
US7380163B2 (en) * | 2003-04-23 | 2008-05-27 | Dot Hill Systems Corporation | Apparatus and method for deterministically performing active-active failover of redundant servers in response to a heartbeat link failure |
US20050075729A1 (en) * | 2003-10-06 | 2005-04-07 | Nguyen Tuoc Tan | Minimally invasive valve replacement system |
DE10350287A1 (en) * | 2003-10-24 | 2005-05-25 | Deutsche Institute für Textil- und Faserforschung Stuttgart - Stiftung des öffentlichen Rechts | Cardiovascular implant, for use as a vascular or heart valve replacement, comprises a non-resorbable polymer formed as a microfiber fleece that allows colonization by a cells |
US7445631B2 (en) | 2003-12-23 | 2008-11-04 | Sadra Medical, Inc. | Methods and apparatus for endovascularly replacing a patient's heart valve |
US20050137694A1 (en) | 2003-12-23 | 2005-06-23 | Haug Ulrich R. | Methods and apparatus for endovascularly replacing a patient's heart valve |
US8828078B2 (en) * | 2003-12-23 | 2014-09-09 | Sadra Medical, Inc. | Methods and apparatus for endovascular heart valve replacement comprising tissue grasping elements |
US8840663B2 (en) | 2003-12-23 | 2014-09-23 | Sadra Medical, Inc. | Repositionable heart valve method |
US7959666B2 (en) | 2003-12-23 | 2011-06-14 | Sadra Medical, Inc. | Methods and apparatus for endovascularly replacing a heart valve |
US20050137687A1 (en) | 2003-12-23 | 2005-06-23 | Sadra Medical | Heart valve anchor and method |
US8579962B2 (en) | 2003-12-23 | 2013-11-12 | Sadra Medical, Inc. | Methods and apparatus for performing valvuloplasty |
US8603160B2 (en) | 2003-12-23 | 2013-12-10 | Sadra Medical, Inc. | Method of using a retrievable heart valve anchor with a sheath |
US20120041550A1 (en) | 2003-12-23 | 2012-02-16 | Sadra Medical, Inc. | Methods and Apparatus for Endovascular Heart Valve Replacement Comprising Tissue Grasping Elements |
US9005273B2 (en) * | 2003-12-23 | 2015-04-14 | Sadra Medical, Inc. | Assessing the location and performance of replacement heart valves |
US8182528B2 (en) | 2003-12-23 | 2012-05-22 | Sadra Medical, Inc. | Locking heart valve anchor |
US8343213B2 (en) | 2003-12-23 | 2013-01-01 | Sadra Medical, Inc. | Leaflet engagement elements and methods for use thereof |
US7381219B2 (en) | 2003-12-23 | 2008-06-03 | Sadra Medical, Inc. | Low profile heart valve and delivery system |
US11278398B2 (en) | 2003-12-23 | 2022-03-22 | Boston Scientific Scimed, Inc. | Methods and apparatus for endovascular heart valve replacement comprising tissue grasping elements |
US9526609B2 (en) * | 2003-12-23 | 2016-12-27 | Boston Scientific Scimed, Inc. | Methods and apparatus for endovascularly replacing a patient's heart valve |
US7780725B2 (en) | 2004-06-16 | 2010-08-24 | Sadra Medical, Inc. | Everting heart valve |
US7803178B2 (en) | 2004-01-30 | 2010-09-28 | Trivascular, Inc. | Inflatable porous implants and methods for drug delivery |
JP4403183B2 (en) * | 2004-02-05 | 2010-01-20 | チルドレンズ・メディカル・センター・コーポレイション | Transcatheter delivery of replacement heart valves |
ITTO20040135A1 (en) | 2004-03-03 | 2004-06-03 | Sorin Biomedica Cardio Spa | CARDIAC VALVE PROSTHESIS |
US20050228494A1 (en) * | 2004-03-29 | 2005-10-13 | Salvador Marquez | Controlled separation heart valve frame |
EP1737390A1 (en) * | 2004-04-08 | 2007-01-03 | Cook Incorporated | Implantable medical device with optimized shape |
US8361013B2 (en) * | 2004-04-19 | 2013-01-29 | The Invention Science Fund I, Llc | Telescoping perfusion management system |
US9011329B2 (en) | 2004-04-19 | 2015-04-21 | Searete Llc | Lumenally-active device |
US8337482B2 (en) * | 2004-04-19 | 2012-12-25 | The Invention Science Fund I, Llc | System for perfusion management |
US20070010868A1 (en) * | 2004-04-19 | 2007-01-11 | Searete Llc, A Limited Liability Corporation Of The State Of Delaware | Lumenally-active device |
US7850676B2 (en) * | 2004-04-19 | 2010-12-14 | The Invention Science Fund I, Llc | System with a reservoir for perfusion management |
US20050234440A1 (en) * | 2004-04-19 | 2005-10-20 | Searete Llc, A Limited Liability Corporation Of The State Of Delaware | System with a sensor for perfusion management |
US7998060B2 (en) * | 2004-04-19 | 2011-08-16 | The Invention Science Fund I, Llc | Lumen-traveling delivery device |
US8024036B2 (en) | 2007-03-19 | 2011-09-20 | The Invention Science Fund I, Llc | Lumen-traveling biological interface device and method of use |
US20070244520A1 (en) * | 2004-04-19 | 2007-10-18 | Searete Llc | Lumen-traveling biological interface device and method of use |
US8000784B2 (en) | 2004-04-19 | 2011-08-16 | The Invention Science Fund I, Llc | Lumen-traveling device |
US8092549B2 (en) * | 2004-09-24 | 2012-01-10 | The Invention Science Fund I, Llc | Ciliated stent-like-system |
US8353896B2 (en) * | 2004-04-19 | 2013-01-15 | The Invention Science Fund I, Llc | Controllable release nasal system |
US8512219B2 (en) | 2004-04-19 | 2013-08-20 | The Invention Science Fund I, Llc | Bioelectromagnetic interface system |
US20060025857A1 (en) | 2004-04-23 | 2006-02-02 | Bjarne Bergheim | Implantable prosthetic valve |
NL1026076C2 (en) | 2004-04-29 | 2005-11-01 | Univ Eindhoven Tech | Molded part manufactured by means of electro-spinning and a method for the manufacture thereof as well as the use of such a molded part. |
US8012201B2 (en) * | 2004-05-05 | 2011-09-06 | Direct Flow Medical, Inc. | Translumenally implantable heart valve with multiple chamber formed in place support |
FR2874812B1 (en) * | 2004-09-07 | 2007-06-15 | Perouse Soc Par Actions Simpli | INTERCHANGEABLE PROTHETIC VALVE |
CN1745727A (en) * | 2004-09-08 | 2006-03-15 | 王蓉珍 | Intercurrent artificial heart valve, its implanting and recovering device |
AU2005296053B2 (en) * | 2004-10-18 | 2011-03-10 | Covidien Lp | Compression anastomosis device and method |
EP1830747A2 (en) * | 2004-11-19 | 2007-09-12 | Medtronic, Inc. | Method and apparatus for treatment of cardiac valves |
US20060116572A1 (en) * | 2004-12-01 | 2006-06-01 | Case Brian C | Sensing delivery system for intraluminal medical devices |
US20060178731A1 (en) * | 2005-02-09 | 2006-08-10 | Numed, Inc. | Apparatus for aiding the flow of blood through patient's circulatory system |
ITTO20050074A1 (en) | 2005-02-10 | 2006-08-11 | Sorin Biomedica Cardio Srl | CARDIAC VALVE PROSTHESIS |
WO2006097931A2 (en) | 2005-03-17 | 2006-09-21 | Valtech Cardio, Ltd. | Mitral valve treatment techniques |
SE531468C2 (en) | 2005-04-21 | 2009-04-14 | Edwards Lifesciences Ag | An apparatus for controlling blood flow |
US7962208B2 (en) | 2005-04-25 | 2011-06-14 | Cardiac Pacemakers, Inc. | Method and apparatus for pacing during revascularization |
EP1895941A1 (en) * | 2005-05-20 | 2008-03-12 | The Cleveland Clinic Foundation | Apparatus and methods for repairing the function of a diseased valve and method for making same |
US8951285B2 (en) | 2005-07-05 | 2015-02-10 | Mitralign, Inc. | Tissue anchor, anchoring system and methods of using the same |
TWI289765B (en) | 2005-07-20 | 2007-11-11 | Quanta Comp Inc | Devices a methods for signal switching and processing |
WO2007013108A1 (en) * | 2005-07-27 | 2007-02-01 | Sango S.A.S Di Cattani Rita E C. | Endovenous stent and venous neovalvular endobioprosthesis |
US20070038295A1 (en) * | 2005-08-12 | 2007-02-15 | Cook Incorporated | Artificial valve prosthesis having a ring frame |
US20070078510A1 (en) | 2005-09-26 | 2007-04-05 | Ryan Timothy R | Prosthetic cardiac and venous valves |
US7503928B2 (en) * | 2005-10-21 | 2009-03-17 | Cook Biotech Incorporated | Artificial valve with center leaflet attachment |
US20070112372A1 (en) * | 2005-11-17 | 2007-05-17 | Stephen Sosnowski | Biodegradable vascular filter |
US20070213813A1 (en) | 2005-12-22 | 2007-09-13 | Symetis Sa | Stent-valves for valve replacement and associated methods and systems for surgery |
US20070179599A1 (en) * | 2006-01-31 | 2007-08-02 | Icon Medical Corp. | Vascular protective device |
CN101415379B (en) | 2006-02-14 | 2012-06-20 | 萨德拉医学公司 | Systems for delivering a medical implant |
US9622850B2 (en) * | 2006-02-28 | 2017-04-18 | C.R. Bard, Inc. | Flexible stretch stent-graft |
WO2007106755A1 (en) * | 2006-03-10 | 2007-09-20 | Arbor Surgical Technologies, Inc. | Valve introducers and methods for making and using them |
US20070239271A1 (en) * | 2006-04-10 | 2007-10-11 | Than Nguyen | Systems and methods for loading a prosthesis onto a minimally invasive delivery system |
US20120035439A1 (en) | 2006-04-12 | 2012-02-09 | Bran Ferren | Map-based navigation of a body tube tree by a lumen traveling device |
US20070244545A1 (en) * | 2006-04-14 | 2007-10-18 | Medtronic Vascular, Inc. | Prosthetic Conduit With Radiopaque Symmetry Indicators |
EP1849440A1 (en) * | 2006-04-28 | 2007-10-31 | Younes Boudjemline | Vascular stents with varying diameter |
JP2009536074A (en) * | 2006-05-05 | 2009-10-08 | チルドレンズ・メディカル・センター・コーポレイション | Transcatheter heart valve |
US8092517B2 (en) * | 2006-05-25 | 2012-01-10 | Deep Vein Medical, Inc. | Device for regulating blood flow |
US8109993B2 (en) * | 2006-05-25 | 2012-02-07 | Deep Vein Medical, Inc. | Device for regulating blood flow |
US7811316B2 (en) * | 2006-05-25 | 2010-10-12 | Deep Vein Medical, Inc. | Device for regulating blood flow |
WO2007140320A2 (en) | 2006-05-26 | 2007-12-06 | Nanyang Technological University | Implantable article, method of forming same and method for reducing thrombogenicity |
JP5222290B2 (en) * | 2006-07-19 | 2013-06-26 | ノベート・メディカル・リミテッド | Blood vessel filter |
WO2008047354A2 (en) | 2006-10-16 | 2008-04-24 | Ventor Technologies Ltd. | Transapical delivery system with ventriculo-arterial overflow bypass |
US7771467B2 (en) | 2006-11-03 | 2010-08-10 | The Cleveland Clinic Foundation | Apparatus for repairing the function of a native aortic valve |
US20080109064A1 (en) * | 2006-11-03 | 2008-05-08 | Medtronic Vascular, Inc. | Methods and Devices for Biological Fixation of Stent Grafts |
EP2097119A4 (en) * | 2006-11-21 | 2012-10-17 | Abbott Lab | Use of a terpolymer of tetrafluoroethylene, hexafluoropropylene, and vinylidene fluoride in drug eluting coatings |
US11259924B2 (en) | 2006-12-05 | 2022-03-01 | Valtech Cardio Ltd. | Implantation of repair devices in the heart |
US9883943B2 (en) | 2006-12-05 | 2018-02-06 | Valtech Cardio, Ltd. | Implantation of repair devices in the heart |
JP5593545B2 (en) | 2006-12-06 | 2014-09-24 | メドトロニック シーブイ ルクセンブルク エス.アー.エール.エル. | System and method for transapical delivery of a self-expanding valve secured to an annulus |
US20080269877A1 (en) * | 2007-02-05 | 2008-10-30 | Jenson Mark L | Systems and methods for valve delivery |
CA2677633C (en) * | 2007-02-15 | 2015-09-08 | Medtronic, Inc. | Multi-layered stents and methods of implanting |
WO2008101083A2 (en) | 2007-02-15 | 2008-08-21 | Cook Incorporated | Artificial valve prostheses with a free leaflet portion |
WO2008098777A1 (en) | 2007-02-16 | 2008-08-21 | Universität Zürich | Tubular supporting prosthesis having a heart valve, particularly for aortic valve replacement |
EP1958597A1 (en) * | 2007-02-16 | 2008-08-20 | Universität Zürich | Tubular support implant with heart valve in particular for aorta valve replacement |
WO2008103280A2 (en) * | 2007-02-16 | 2008-08-28 | Medtronic, Inc. | Delivery systems and methods of implantation for replacement prosthetic heart valves |
US11660190B2 (en) | 2007-03-13 | 2023-05-30 | Edwards Lifesciences Corporation | Tissue anchors, systems and methods, and devices |
FR2915087B1 (en) | 2007-04-20 | 2021-11-26 | Corevalve Inc | IMPLANT FOR TREATMENT OF A HEART VALVE, IN PARTICULAR OF A MITRAL VALVE, EQUIPMENT INCLUDING THIS IMPLANT AND MATERIAL FOR PLACING THIS IMPLANT. |
US8747458B2 (en) | 2007-08-20 | 2014-06-10 | Medtronic Ventor Technologies Ltd. | Stent loading tool and method for use thereof |
ES2586121T3 (en) | 2007-08-21 | 2016-10-11 | Symetis Sa | Replacement valve |
EP2194921B1 (en) | 2007-10-04 | 2018-08-29 | TriVascular, Inc. | Modular vascular graft for low profile percutaneous delivery |
US10856970B2 (en) | 2007-10-10 | 2020-12-08 | Medtronic Ventor Technologies Ltd. | Prosthetic heart valve for transfemoral delivery |
US9848981B2 (en) | 2007-10-12 | 2017-12-26 | Mayo Foundation For Medical Education And Research | Expandable valve prosthesis with sealing mechanism |
US20090105813A1 (en) * | 2007-10-17 | 2009-04-23 | Sean Chambers | Implantable valve device |
WO2009053497A1 (en) * | 2007-10-25 | 2009-04-30 | Symetis Sa | Stents, valved-stents and methods and systems for delivery thereof |
WO2009067432A1 (en) * | 2007-11-19 | 2009-05-28 | Cook Incorporated | Valve frame |
US20110230954A1 (en) * | 2009-06-11 | 2011-09-22 | Peter Schneider | Stent device having focal elevating elements for minimal surface area contact with lumen walls |
US8128677B2 (en) * | 2007-12-12 | 2012-03-06 | Intact Vascular LLC | Device and method for tacking plaque to a blood vessel wall |
US9603730B2 (en) | 2007-12-12 | 2017-03-28 | Intact Vascular, Inc. | Endoluminal device and method |
US10166127B2 (en) | 2007-12-12 | 2019-01-01 | Intact Vascular, Inc. | Endoluminal device and method |
US9375327B2 (en) | 2007-12-12 | 2016-06-28 | Intact Vascular, Inc. | Endovascular implant |
US7896911B2 (en) * | 2007-12-12 | 2011-03-01 | Innovasc Llc | Device and method for tacking plaque to blood vessel wall |
US10022250B2 (en) | 2007-12-12 | 2018-07-17 | Intact Vascular, Inc. | Deployment device for placement of multiple intraluminal surgical staples |
US20090171456A1 (en) * | 2007-12-28 | 2009-07-02 | Kveen Graig L | Percutaneous heart valve, system, and method |
US8211165B1 (en) | 2008-01-08 | 2012-07-03 | Cook Medical Technologies Llc | Implantable device for placement in a vessel having a variable size |
US9393115B2 (en) * | 2008-01-24 | 2016-07-19 | Medtronic, Inc. | Delivery systems and methods of implantation for prosthetic heart valves |
US9149358B2 (en) * | 2008-01-24 | 2015-10-06 | Medtronic, Inc. | Delivery systems for prosthetic heart valves |
US20090287290A1 (en) * | 2008-01-24 | 2009-11-19 | Medtronic, Inc. | Delivery Systems and Methods of Implantation for Prosthetic Heart Valves |
US9241792B2 (en) * | 2008-02-29 | 2016-01-26 | Edwards Lifesciences Corporation | Two-step heart valve implantation |
US8382829B1 (en) | 2008-03-10 | 2013-02-26 | Mitralign, Inc. | Method to reduce mitral regurgitation by cinching the commissure of the mitral valve |
US8430927B2 (en) * | 2008-04-08 | 2013-04-30 | Medtronic, Inc. | Multiple orifice implantable heart valve and methods of implantation |
EP3141219A1 (en) | 2008-04-23 | 2017-03-15 | Medtronic, Inc. | Stented heart valve devices |
JP5685183B2 (en) * | 2008-04-23 | 2015-03-18 | メドトロニック,インコーポレイテッド | Heart valve device with stent |
US20090276040A1 (en) | 2008-05-01 | 2009-11-05 | Edwards Lifesciences Corporation | Device and method for replacing mitral valve |
US8840661B2 (en) * | 2008-05-16 | 2014-09-23 | Sorin Group Italia S.R.L. | Atraumatic prosthetic heart valve prosthesis |
US8206636B2 (en) | 2008-06-20 | 2012-06-26 | Amaranth Medical Pte. | Stent fabrication via tubular casting processes |
US8206635B2 (en) * | 2008-06-20 | 2012-06-26 | Amaranth Medical Pte. | Stent fabrication via tubular casting processes |
US10898620B2 (en) | 2008-06-20 | 2021-01-26 | Razmodics Llc | Composite stent having multi-axial flexibility and method of manufacture thereof |
US20110208299A1 (en) | 2008-08-19 | 2011-08-25 | Roelof Marissen | Implantable valve prosthesis and method for manufacturing such a valve |
WO2010031060A1 (en) | 2008-09-15 | 2010-03-18 | Medtronic Ventor Technologies Ltd. | Prosthetic heart valve having identifiers for aiding in radiographic positioning |
US8721714B2 (en) | 2008-09-17 | 2014-05-13 | Medtronic Corevalve Llc | Delivery system for deployment of medical devices |
JP5607639B2 (en) | 2008-10-10 | 2014-10-15 | サドラ メディカル インコーポレイテッド | Medical devices and systems |
US8137398B2 (en) * | 2008-10-13 | 2012-03-20 | Medtronic Ventor Technologies Ltd | Prosthetic valve having tapered tip when compressed for delivery |
US8986361B2 (en) | 2008-10-17 | 2015-03-24 | Medtronic Corevalve, Inc. | Delivery system for deployment of medical devices |
US8715342B2 (en) | 2009-05-07 | 2014-05-06 | Valtech Cardio, Ltd. | Annuloplasty ring with intra-ring anchoring |
US8545553B2 (en) | 2009-05-04 | 2013-10-01 | Valtech Cardio, Ltd. | Over-wire rotation tool |
US10517719B2 (en) | 2008-12-22 | 2019-12-31 | Valtech Cardio, Ltd. | Implantation of repair devices in the heart |
US8241351B2 (en) | 2008-12-22 | 2012-08-14 | Valtech Cardio, Ltd. | Adjustable partial annuloplasty ring and mechanism therefor |
WO2010073246A2 (en) | 2008-12-22 | 2010-07-01 | Valtech Cardio, Ltd. | Adjustable annuloplasty devices and adjustment mechanisms therefor |
ES2551694T3 (en) | 2008-12-23 | 2015-11-23 | Sorin Group Italia S.R.L. | Expandable prosthetic valve with anchoring appendages |
US20100228281A1 (en) | 2009-01-16 | 2010-09-09 | Paul Gilson | Vascular filter system |
US8057507B2 (en) | 2009-01-16 | 2011-11-15 | Novate Medical Limited | Vascular filter |
JP5643226B2 (en) * | 2009-01-16 | 2014-12-17 | ノベート・メディカル・リミテッド | Vascular filter device |
US8668713B2 (en) * | 2009-01-16 | 2014-03-11 | Novate Medical Limited | Vascular filter device |
CN102282301B (en) * | 2009-01-16 | 2014-07-30 | Zeus工业品公司 | Electrospinning of ptfe with high viscosity materials |
US8353956B2 (en) | 2009-02-17 | 2013-01-15 | Valtech Cardio, Ltd. | Actively-engageable movement-restriction mechanism for use with an annuloplasty structure |
EP2628465A1 (en) | 2009-04-27 | 2013-08-21 | Sorin Group Italia S.r.l. | Prosthetic vascular conduit |
US9968452B2 (en) | 2009-05-04 | 2018-05-15 | Valtech Cardio, Ltd. | Annuloplasty ring delivery cathethers |
US8808369B2 (en) * | 2009-10-05 | 2014-08-19 | Mayo Foundation For Medical Education And Research | Minimally invasive aortic valve replacement |
US9180007B2 (en) | 2009-10-29 | 2015-11-10 | Valtech Cardio, Ltd. | Apparatus and method for guide-wire based advancement of an adjustable implant |
US10098737B2 (en) | 2009-10-29 | 2018-10-16 | Valtech Cardio, Ltd. | Tissue anchor for annuloplasty device |
WO2011067770A1 (en) | 2009-12-02 | 2011-06-09 | Valtech Cardio, Ltd. | Delivery tool for implantation of spool assembly coupled to a helical anchor |
US8870950B2 (en) | 2009-12-08 | 2014-10-28 | Mitral Tech Ltd. | Rotation-based anchoring of an implant |
WO2011097402A1 (en) * | 2010-02-05 | 2011-08-11 | Stryker Nv Operations Limited | Multimode occlusion and stenosis treatment apparatus and method of use |
US9226826B2 (en) * | 2010-02-24 | 2016-01-05 | Medtronic, Inc. | Transcatheter valve structure and methods for valve delivery |
US20110224785A1 (en) | 2010-03-10 | 2011-09-15 | Hacohen Gil | Prosthetic mitral valve with tissue anchors |
WO2011115799A2 (en) | 2010-03-17 | 2011-09-22 | Deep Vein Medical, Inc. | Fatigue-resistant flow regulating device and manufacturing methods |
US8579964B2 (en) | 2010-05-05 | 2013-11-12 | Neovasc Inc. | Transcatheter mitral valve prosthesis |
IT1400327B1 (en) | 2010-05-21 | 2013-05-24 | Sorin Biomedica Cardio Srl | SUPPORT DEVICE FOR VALVULAR PROSTHESIS AND CORRESPONDING CORRESPONDENT. |
CA2801111A1 (en) * | 2010-06-02 | 2011-12-08 | Nonwotecc Medical Gmbh | Device for placement in a hollow organ, in particular for holding open said hollow organ and method for producing such device |
WO2012006124A2 (en) | 2010-06-28 | 2012-01-12 | Vela Biosystems Llc | Method and apparatus for the endoluminal delivery of intravascular devices |
US11653910B2 (en) | 2010-07-21 | 2023-05-23 | Cardiovalve Ltd. | Helical anchor implantation |
US9763657B2 (en) | 2010-07-21 | 2017-09-19 | Mitraltech Ltd. | Techniques for percutaneous mitral valve replacement and sealing |
EP2611388B1 (en) | 2010-09-01 | 2022-04-27 | Medtronic Vascular Galway | Prosthetic valve support structure |
CA2808673C (en) | 2010-09-10 | 2019-07-02 | Symetis Sa | Valve replacement devices, delivery device for a valve replacement device and method of production of a valve replacement device |
AU2011343755A1 (en) | 2010-12-14 | 2013-06-06 | Colibri Heart Valve Llc | Percutaneously deliverable heart valve including folded membrane cusps with integral leaflets |
US20130018215A1 (en) * | 2011-01-18 | 2013-01-17 | Merit Medical Systems, Inc. | Esophageal stent and methods for use of same |
EP2486894B1 (en) | 2011-02-14 | 2021-06-09 | Sorin Group Italia S.r.l. | Sutureless anchoring device for cardiac valve prostheses |
EP2486893B1 (en) | 2011-02-14 | 2017-07-05 | Sorin Group Italia S.r.l. | Sutureless anchoring device for cardiac valve prostheses |
US9554900B2 (en) | 2011-04-01 | 2017-01-31 | W. L. Gore & Associates, Inc. | Durable high strength polymer composites suitable for implant and articles produced therefrom |
US9801712B2 (en) | 2011-04-01 | 2017-10-31 | W. L. Gore & Associates, Inc. | Coherent single layer high strength synthetic polymer composites for prosthetic valves |
US9744033B2 (en) | 2011-04-01 | 2017-08-29 | W.L. Gore & Associates, Inc. | Elastomeric leaflet for prosthetic heart valves |
US20130197631A1 (en) | 2011-04-01 | 2013-08-01 | W. L. Gore & Associates, Inc. | Durable multi-layer high strength polymer composite suitable for implant and articles produced therefrom |
US8961599B2 (en) * | 2011-04-01 | 2015-02-24 | W. L. Gore & Associates, Inc. | Durable high strength polymer composite suitable for implant and articles produced therefrom |
US8945212B2 (en) | 2011-04-01 | 2015-02-03 | W. L. Gore & Associates, Inc. | Durable multi-layer high strength polymer composite suitable for implant and articles produced therefrom |
US9308087B2 (en) | 2011-04-28 | 2016-04-12 | Neovasc Tiara Inc. | Sequentially deployed transcatheter mitral valve prosthesis |
US9554897B2 (en) | 2011-04-28 | 2017-01-31 | Neovasc Tiara Inc. | Methods and apparatus for engaging a valve prosthesis with tissue |
WO2012151088A1 (en) * | 2011-05-02 | 2012-11-08 | Cook Medical Technologies Llc | Biodegradable, bioabsorbable stent anchors |
EP2520251A1 (en) | 2011-05-05 | 2012-11-07 | Symetis SA | Method and Apparatus for Compressing Stent-Valves |
AU2016202250A1 (en) * | 2011-06-01 | 2016-05-05 | W. L. Gore & Associates, Inc. | Durable multi-layer high strength polymer composite suitable for implant and articles produced therefrom |
US10285798B2 (en) | 2011-06-03 | 2019-05-14 | Merit Medical Systems, Inc. | Esophageal stent |
US10285831B2 (en) | 2011-06-03 | 2019-05-14 | Intact Vascular, Inc. | Endovascular implant |
US10792152B2 (en) | 2011-06-23 | 2020-10-06 | Valtech Cardio, Ltd. | Closed band for percutaneous annuloplasty |
US9918840B2 (en) | 2011-06-23 | 2018-03-20 | Valtech Cardio, Ltd. | Closed band for percutaneous annuloplasty |
WO2013009975A1 (en) | 2011-07-12 | 2013-01-17 | Boston Scientific Scimed, Inc. | Coupling system for medical devices |
EP3417813B1 (en) | 2011-08-05 | 2020-05-13 | Cardiovalve Ltd | Percutaneous mitral valve replacement |
WO2013021374A2 (en) | 2011-08-05 | 2013-02-14 | Mitraltech Ltd. | Techniques for percutaneous mitral valve replacement and sealing |
US8852272B2 (en) | 2011-08-05 | 2014-10-07 | Mitraltech Ltd. | Techniques for percutaneous mitral valve replacement and sealing |
US20140324164A1 (en) | 2011-08-05 | 2014-10-30 | Mitraltech Ltd. | Techniques for percutaneous mitral valve replacement and sealing |
US9554806B2 (en) | 2011-09-16 | 2017-01-31 | W. L. Gore & Associates, Inc. | Occlusive devices |
US8986368B2 (en) | 2011-10-31 | 2015-03-24 | Merit Medical Systems, Inc. | Esophageal stent with valve |
US8858623B2 (en) | 2011-11-04 | 2014-10-14 | Valtech Cardio, Ltd. | Implant having multiple rotational assemblies |
EP3656434B1 (en) | 2011-11-08 | 2021-10-20 | Valtech Cardio, Ltd. | Controlled steering functionality for implant-delivery tool |
US8951243B2 (en) | 2011-12-03 | 2015-02-10 | Boston Scientific Scimed, Inc. | Medical device handle |
AU2012358255B2 (en) * | 2011-12-23 | 2017-02-16 | Abiomed, Inc. | Heart valve prosthesis with open stent |
EP2842517A1 (en) * | 2011-12-29 | 2015-03-04 | Sorin Group Italia S.r.l. | A kit for implanting prosthetic vascular conduits |
US10172708B2 (en) | 2012-01-25 | 2019-01-08 | Boston Scientific Scimed, Inc. | Valve assembly with a bioabsorbable gasket and a replaceable valve implant |
EP3733134A1 (en) | 2012-01-25 | 2020-11-04 | Intact Vascular, Inc. | Endoluminal device |
US20130274873A1 (en) | 2012-03-22 | 2013-10-17 | Symetis Sa | Transcatheter Stent-Valves and Methods, Systems and Devices for Addressing Para-Valve Leakage |
US11207176B2 (en) | 2012-03-22 | 2021-12-28 | Boston Scientific Scimed, Inc. | Transcatheter stent-valves and methods, systems and devices for addressing para-valve leakage |
US8992595B2 (en) | 2012-04-04 | 2015-03-31 | Trivascular, Inc. | Durable stent graft with tapered struts and stable delivery methods and devices |
US9498363B2 (en) | 2012-04-06 | 2016-11-22 | Trivascular, Inc. | Delivery catheter for endovascular device |
US9011515B2 (en) | 2012-04-19 | 2015-04-21 | Caisson Interventional, LLC | Heart valve assembly systems and methods |
US9427315B2 (en) | 2012-04-19 | 2016-08-30 | Caisson Interventional, LLC | Valve replacement systems and methods |
US9345573B2 (en) | 2012-05-30 | 2016-05-24 | Neovasc Tiara Inc. | Methods and apparatus for loading a prosthesis onto a delivery system |
EP2854718B1 (en) | 2012-06-05 | 2017-03-22 | Merit Medical Systems, Inc. | Esophageal stent |
US9883941B2 (en) | 2012-06-19 | 2018-02-06 | Boston Scientific Scimed, Inc. | Replacement heart valve |
CN102787448B (en) * | 2012-07-26 | 2015-06-03 | 东华大学 | Preparation method of degradable polycarbonate butanediol ester electrospinning fiber films |
WO2014052818A1 (en) | 2012-09-29 | 2014-04-03 | Mitralign, Inc. | Plication lock delivery system and method of use thereof |
WO2014064695A2 (en) | 2012-10-23 | 2014-05-01 | Valtech Cardio, Ltd. | Percutaneous tissue anchor techniques |
EP3730084A1 (en) | 2012-10-23 | 2020-10-28 | Valtech Cardio, Ltd. | Controlled steering functionality for implant-delivery tool |
US8628571B1 (en) | 2012-11-13 | 2014-01-14 | Mitraltech Ltd. | Percutaneously-deliverable mechanical valve |
WO2014087402A1 (en) | 2012-12-06 | 2014-06-12 | Valtech Cardio, Ltd. | Techniques for guide-wire based advancement of a tool |
US20150351906A1 (en) | 2013-01-24 | 2015-12-10 | Mitraltech Ltd. | Ventricularly-anchored prosthetic valves |
EP2953578A4 (en) | 2013-02-08 | 2016-11-02 | Muffin Inc | Peripheral sealing venous check-valve |
US9724084B2 (en) | 2013-02-26 | 2017-08-08 | Mitralign, Inc. | Devices and methods for percutaneous tricuspid valve repair |
US8709076B1 (en) * | 2013-03-01 | 2014-04-29 | Cormatrix Cardiovascular, Inc. | Two-piece prosthetic valve |
CA2891225C (en) | 2013-03-05 | 2021-03-02 | Merit Medical Systems, Inc. | Reinforced valve |
US10449333B2 (en) | 2013-03-14 | 2019-10-22 | Valtech Cardio, Ltd. | Guidewire feeder |
JP2016509909A (en) | 2013-03-15 | 2016-04-04 | ノベート・メディカル・リミテッド | Vascular filter device |
WO2014150130A1 (en) | 2013-03-15 | 2014-09-25 | Merit Medical Systems, Inc. | Esophageal stent |
CN105283214B (en) | 2013-03-15 | 2018-10-16 | 北京泰德制药股份有限公司 | Translate conduit, system and its application method |
US9572665B2 (en) | 2013-04-04 | 2017-02-21 | Neovasc Tiara Inc. | Methods and apparatus for delivering a prosthetic valve to a beating heart |
EP2991586A1 (en) | 2013-05-03 | 2016-03-09 | Medtronic Inc. | Valve delivery tool |
US11911258B2 (en) | 2013-06-26 | 2024-02-27 | W. L. Gore & Associates, Inc. | Space filling devices |
US10070857B2 (en) | 2013-08-31 | 2018-09-11 | Mitralign, Inc. | Devices and methods for locating and implanting tissue anchors at mitral valve commissure |
US10299793B2 (en) | 2013-10-23 | 2019-05-28 | Valtech Cardio, Ltd. | Anchor magazine |
US9421094B2 (en) | 2013-10-23 | 2016-08-23 | Caisson Interventional, LLC | Methods and systems for heart valve therapy |
US9610162B2 (en) | 2013-12-26 | 2017-04-04 | Valtech Cardio, Ltd. | Implantation of flexible implant |
US9763778B2 (en) | 2014-03-18 | 2017-09-19 | St. Jude Medical, Cardiology Division, Inc. | Aortic insufficiency valve percutaneous valve anchoring |
US9974647B2 (en) | 2014-06-12 | 2018-05-22 | Caisson Interventional, LLC | Two stage anchor and mitral valve assembly |
EP4066786A1 (en) | 2014-07-30 | 2022-10-05 | Cardiovalve Ltd. | Articulatable prosthetic valve |
WO2016059639A1 (en) | 2014-10-14 | 2016-04-21 | Valtech Cardio Ltd. | Leaflet-restraining techniques |
US9750607B2 (en) | 2014-10-23 | 2017-09-05 | Caisson Interventional, LLC | Systems and methods for heart valve therapy |
US9750605B2 (en) | 2014-10-23 | 2017-09-05 | Caisson Interventional, LLC | Systems and methods for heart valve therapy |
US9901445B2 (en) | 2014-11-21 | 2018-02-27 | Boston Scientific Scimed, Inc. | Valve locking mechanism |
WO2016115375A1 (en) | 2015-01-16 | 2016-07-21 | Boston Scientific Scimed, Inc. | Displacement based lock and release mechanism |
US9861477B2 (en) | 2015-01-26 | 2018-01-09 | Boston Scientific Scimed Inc. | Prosthetic heart valve square leaflet-leaflet stitch |
US9433520B2 (en) | 2015-01-29 | 2016-09-06 | Intact Vascular, Inc. | Delivery device and method of delivery |
US9375336B1 (en) | 2015-01-29 | 2016-06-28 | Intact Vascular, Inc. | Delivery device and method of delivery |
US9788942B2 (en) | 2015-02-03 | 2017-10-17 | Boston Scientific Scimed Inc. | Prosthetic heart valve having tubular seal |
WO2016126524A1 (en) | 2015-02-03 | 2016-08-11 | Boston Scientific Scimed, Inc. | Prosthetic heart valve having tubular seal |
WO2016125160A1 (en) | 2015-02-05 | 2016-08-11 | Mitraltech Ltd. | Prosthetic valve with axially-sliding frames |
US9974651B2 (en) | 2015-02-05 | 2018-05-22 | Mitral Tech Ltd. | Prosthetic valve with axially-sliding frames |
US20160256269A1 (en) | 2015-03-05 | 2016-09-08 | Mitralign, Inc. | Devices for treating paravalvular leakage and methods use thereof |
US10426617B2 (en) | 2015-03-06 | 2019-10-01 | Boston Scientific Scimed, Inc. | Low profile valve locking mechanism and commissure assembly |
US10285809B2 (en) | 2015-03-06 | 2019-05-14 | Boston Scientific Scimed Inc. | TAVI anchoring assist device |
US10080652B2 (en) | 2015-03-13 | 2018-09-25 | Boston Scientific Scimed, Inc. | Prosthetic heart valve having an improved tubular seal |
US10441416B2 (en) * | 2015-04-21 | 2019-10-15 | Edwards Lifesciences Corporation | Percutaneous mitral valve replacement device |
CN114515173A (en) | 2015-04-30 | 2022-05-20 | 瓦尔泰克卡迪欧有限公司 | Valvuloplasty techniques |
ES2908460T3 (en) | 2015-05-14 | 2022-04-29 | Gore & Ass | Devices for occlusion of an atrial appendage |
CN107847323B (en) * | 2015-06-01 | 2020-04-24 | 爱德华兹生命科学公司 | Heart valve repair device configured for percutaneous delivery |
WO2017004377A1 (en) | 2015-07-02 | 2017-01-05 | Boston Scientific Scimed, Inc. | Adjustable nosecone |
US10195392B2 (en) | 2015-07-02 | 2019-02-05 | Boston Scientific Scimed, Inc. | Clip-on catheter |
US10179041B2 (en) | 2015-08-12 | 2019-01-15 | Boston Scientific Scimed Icn. | Pinless release mechanism |
US10136991B2 (en) | 2015-08-12 | 2018-11-27 | Boston Scientific Scimed Inc. | Replacement heart valve implant |
WO2017117370A2 (en) | 2015-12-30 | 2017-07-06 | Mitralign, Inc. | System and method for reducing tricuspid regurgitation |
AU2016380345B2 (en) | 2015-12-30 | 2021-10-28 | Caisson Interventional, LLC | Systems and methods for heart valve therapy |
US10751182B2 (en) | 2015-12-30 | 2020-08-25 | Edwards Lifesciences Corporation | System and method for reshaping right heart |
US10993824B2 (en) | 2016-01-01 | 2021-05-04 | Intact Vascular, Inc. | Delivery device and method of delivery |
CA3007670A1 (en) | 2016-01-29 | 2017-08-03 | Neovasc Tiara Inc. | Prosthetic valve for avoiding obstruction of outflow |
US10342660B2 (en) | 2016-02-02 | 2019-07-09 | Boston Scientific Inc. | Tensioned sheathing aids |
US10531866B2 (en) | 2016-02-16 | 2020-01-14 | Cardiovalve Ltd. | Techniques for providing a replacement valve and transseptal communication |
US10583005B2 (en) | 2016-05-13 | 2020-03-10 | Boston Scientific Scimed, Inc. | Medical device handle |
US10201416B2 (en) | 2016-05-16 | 2019-02-12 | Boston Scientific Scimed, Inc. | Replacement heart valve implant with invertible leaflets |
US10702274B2 (en) | 2016-05-26 | 2020-07-07 | Edwards Lifesciences Corporation | Method and system for closing left atrial appendage |
GB201611910D0 (en) | 2016-07-08 | 2016-08-24 | Valtech Cardio Ltd | Adjustable annuloplasty device with alternating peaks and troughs |
USD800908S1 (en) | 2016-08-10 | 2017-10-24 | Mitraltech Ltd. | Prosthetic valve element |
EP3848003A1 (en) | 2016-08-10 | 2021-07-14 | Cardiovalve Ltd. | Prosthetic valve with concentric frames |
WO2018090148A1 (en) | 2016-11-21 | 2018-05-24 | Neovasc Tiara Inc. | Methods and systems for rapid retraction of a transcatheter heart valve delivery system |
US11045627B2 (en) | 2017-04-18 | 2021-06-29 | Edwards Lifesciences Corporation | Catheter system with linear actuation control mechanism |
WO2018226915A1 (en) | 2017-06-08 | 2018-12-13 | Boston Scientific Scimed, Inc. | Heart valve implant commissure support structure |
US11660218B2 (en) | 2017-07-26 | 2023-05-30 | Intact Vascular, Inc. | Delivery device and method of delivery |
CN111163729B (en) | 2017-08-01 | 2022-03-29 | 波士顿科学国际有限公司 | Medical implant locking mechanism |
US11793633B2 (en) | 2017-08-03 | 2023-10-24 | Cardiovalve Ltd. | Prosthetic heart valve |
US10575948B2 (en) | 2017-08-03 | 2020-03-03 | Cardiovalve Ltd. | Prosthetic heart valve |
US10537426B2 (en) | 2017-08-03 | 2020-01-21 | Cardiovalve Ltd. | Prosthetic heart valve |
US11246704B2 (en) | 2017-08-03 | 2022-02-15 | Cardiovalve Ltd. | Prosthetic heart valve |
US10888421B2 (en) | 2017-09-19 | 2021-01-12 | Cardiovalve Ltd. | Prosthetic heart valve with pouch |
US10939996B2 (en) | 2017-08-16 | 2021-03-09 | Boston Scientific Scimed, Inc. | Replacement heart valve commissure assembly |
CA3073834A1 (en) | 2017-08-25 | 2019-02-28 | Neovasc Tiara Inc. | Sequentially deployed transcatheter mitral valve prosthesis |
WO2019051476A1 (en) | 2017-09-11 | 2019-03-14 | Incubar, LLC | Conduit vascular implant sealing device for reducing endoleak |
US11173023B2 (en) | 2017-10-16 | 2021-11-16 | W. L. Gore & Associates, Inc. | Medical devices and anchors therefor |
US10835221B2 (en) | 2017-11-02 | 2020-11-17 | Valtech Cardio, Ltd. | Implant-cinching devices and systems |
US11135062B2 (en) | 2017-11-20 | 2021-10-05 | Valtech Cardio Ltd. | Cinching of dilated heart muscle |
GB201720803D0 (en) | 2017-12-13 | 2018-01-24 | Mitraltech Ltd | Prosthetic Valve and delivery tool therefor |
GB201800399D0 (en) | 2018-01-10 | 2018-02-21 | Mitraltech Ltd | Temperature-control during crimping of an implant |
US11246625B2 (en) | 2018-01-19 | 2022-02-15 | Boston Scientific Scimed, Inc. | Medical device delivery system with feedback loop |
JP7055882B2 (en) | 2018-01-19 | 2022-04-18 | 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 | Guidance mode indwelling sensor for transcatheter valve system |
CN116531147A (en) | 2018-01-24 | 2023-08-04 | 爱德华兹生命科学创新(以色列)有限公司 | Contraction of annuloplasty structures |
EP3743014B1 (en) | 2018-01-26 | 2023-07-19 | Edwards Lifesciences Innovation (Israel) Ltd. | Techniques for facilitating heart valve tethering and chord replacement |
US11147668B2 (en) | 2018-02-07 | 2021-10-19 | Boston Scientific Scimed, Inc. | Medical device delivery system with alignment feature |
WO2019165394A1 (en) | 2018-02-26 | 2019-08-29 | Boston Scientific Scimed, Inc. | Embedded radiopaque marker in adaptive seal |
CN112399836A (en) | 2018-05-15 | 2021-02-23 | 波士顿科学国际有限公司 | Replacement heart valve commissure assemblies |
WO2019224577A1 (en) | 2018-05-23 | 2019-11-28 | Sorin Group Italia S.R.L. | A cardiac valve prosthesis |
US11241310B2 (en) | 2018-06-13 | 2022-02-08 | Boston Scientific Scimed, Inc. | Replacement heart valve delivery device |
CR20210020A (en) | 2018-07-12 | 2021-07-21 | Valtech Cardio Ltd | Annuloplasty systems and locking tools therefor |
CN109106485B (en) * | 2018-08-31 | 2020-02-07 | 高峰 | Trans-valvular anchoring device for aortic valve retention |
EP3876870B1 (en) | 2018-11-08 | 2023-12-20 | Neovasc Tiara Inc. | Ventricular deployment of a transcatheter mitral valve prosthesis |
WO2020123486A1 (en) | 2018-12-10 | 2020-06-18 | Boston Scientific Scimed, Inc. | Medical device delivery system including a resistance member |
KR20210105434A (en) * | 2019-01-11 | 2021-08-26 | 오레곤 헬스 앤드 사이언스 유니버시티 | Expandable stents to manage venous stenosis |
CA3135753C (en) | 2019-04-01 | 2023-10-24 | Neovasc Tiara Inc. | Controllably deployable prosthetic valve |
US11491006B2 (en) | 2019-04-10 | 2022-11-08 | Neovasc Tiara Inc. | Prosthetic valve with natural blood flow |
US11439504B2 (en) | 2019-05-10 | 2022-09-13 | Boston Scientific Scimed, Inc. | Replacement heart valve with improved cusp washout and reduced loading |
AU2020279750B2 (en) | 2019-05-20 | 2023-07-13 | Neovasc Tiara Inc. | Introducer with hemostasis mechanism |
EP3986332A4 (en) | 2019-06-20 | 2023-07-19 | Neovasc Tiara Inc. | Low profile prosthetic mitral valve |
CA3142906A1 (en) | 2019-10-29 | 2021-05-06 | Valtech Cardio, Ltd. | Annuloplasty and tissue anchor technologies |
US20210154006A1 (en) * | 2019-11-26 | 2021-05-27 | Boston Scientific Limited | Composite web-polymer heart valve |
CN113855349B (en) * | 2020-06-29 | 2023-11-17 | 先健科技(深圳)有限公司 | Lumen stent |
CN112274306B (en) * | 2020-10-08 | 2022-04-05 | 苏州法兰克曼医疗器械有限公司 | Ready-package is used for biliary tract drainage support of treatment |
Citations (68)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US554185A (en) * | 1896-02-04 | George m | ||
US4323525A (en) * | 1978-04-19 | 1982-04-06 | Imperial Chemical Industries Limited | Electrostatic spinning of tubular products |
US4692164A (en) * | 1986-03-06 | 1987-09-08 | Moskovskoe Vysshee Tekhnicheskoe Uchilische, Imeni N.E. Baumana | Bioprosthetic heart valve, methods and device for preparation thereof |
US4725274A (en) * | 1986-10-24 | 1988-02-16 | Baxter Travenol Laboratories, Inc. | Prosthetic heart valve |
US4790843A (en) * | 1986-06-16 | 1988-12-13 | Baxter Travenol Laboratories, Inc. | Prosthetic heart valve assembly |
US4851000A (en) * | 1987-07-31 | 1989-07-25 | Pacific Biomedical Holdings, Ltd. | Bioprosthetic valve stent |
US4892541A (en) * | 1982-11-29 | 1990-01-09 | Tascon Medical Technology Corporation | Heart valve prosthesis |
US4969896A (en) * | 1989-02-01 | 1990-11-13 | Interpore International | Vascular graft prosthesis and method of making the same |
US5032128A (en) * | 1988-07-07 | 1991-07-16 | Medtronic, Inc. | Heart valve prosthesis |
US5037434A (en) * | 1990-04-11 | 1991-08-06 | Carbomedics, Inc. | Bioprosthetic heart valve with elastic commissures |
US5123919A (en) * | 1991-11-21 | 1992-06-23 | Carbomedics, Inc. | Combined prosthetic aortic heart valve and vascular graft |
US5147391A (en) * | 1990-04-11 | 1992-09-15 | Carbomedics, Inc. | Bioprosthetic heart valve with semi-permeable commissure posts and deformable leaflets |
US5156621A (en) * | 1988-03-22 | 1992-10-20 | Navia Jose A | Stentless bioprosthetic cardiac valve |
US5163953A (en) * | 1992-02-10 | 1992-11-17 | Vince Dennis J | Toroidal artificial heart valve stent |
US5163955A (en) * | 1991-01-24 | 1992-11-17 | Autogenics | Rapid assembly, concentric mating stent, tissue heart valve with enhanced clamping and tissue alignment |
US5258023A (en) * | 1992-02-12 | 1993-11-02 | Reger Medical Development, Inc. | Prosthetic heart valve |
US5344442A (en) * | 1991-05-16 | 1994-09-06 | Mures Cardiovasular Research, Inc. | Cardiac valve |
US5358518A (en) * | 1991-06-25 | 1994-10-25 | Sante Camilli | Artificial venous valve |
US5411552A (en) * | 1990-05-18 | 1995-05-02 | Andersen; Henning R. | Valve prothesis for implantation in the body and a catheter for implanting such valve prothesis |
US5415667A (en) * | 1990-06-07 | 1995-05-16 | Frater; Robert W. M. | Mitral heart valve replacements |
US5449384A (en) * | 1992-09-28 | 1995-09-12 | Medtronic, Inc. | Dynamic annulus heart valve employing preserved porcine valve leaflets |
US5449385A (en) * | 1991-05-08 | 1995-09-12 | Nika Health Products Limited | Support for a heart valve prosthesis |
US5480424A (en) * | 1993-11-01 | 1996-01-02 | Cox; James L. | Heart valve replacement using flexible tubes |
US5489298A (en) * | 1991-01-24 | 1996-02-06 | Autogenics | Rapid assembly concentric mating stent, tissue heart valve with enhanced clamping and tissue exposure |
US5500014A (en) * | 1989-05-31 | 1996-03-19 | Baxter International Inc. | Biological valvular prothesis |
US5549665A (en) * | 1993-06-18 | 1996-08-27 | London Health Association | Bioprostethic valve |
US5562729A (en) * | 1994-11-01 | 1996-10-08 | Biocontrol Technology, Inc. | Heart valve |
US5607463A (en) * | 1993-03-30 | 1997-03-04 | Medtronic, Inc. | Intravascular medical device |
US5607465A (en) * | 1993-12-14 | 1997-03-04 | Camilli; Sante | Percutaneous implantable valve for the use in blood vessels |
US5609626A (en) * | 1989-05-31 | 1997-03-11 | Baxter International Inc. | Stent devices and support/restrictor assemblies for use in conjunction with prosthetic vascular grafts |
US5612885A (en) * | 1993-12-17 | 1997-03-18 | Autogenics | Method for constructing a heart valve stent |
US5662713A (en) * | 1991-10-09 | 1997-09-02 | Boston Scientific Corporation | Medical stents for body lumens exhibiting peristaltic motion |
US5695499A (en) * | 1994-10-27 | 1997-12-09 | Schneider (Usa) Inc. | Medical device supported by spirally wound wire |
US5697382A (en) * | 1994-05-05 | 1997-12-16 | Autogenics | Heart valve assembly method |
US5728152A (en) * | 1995-06-07 | 1998-03-17 | St. Jude Medical, Inc. | Bioresorbable heart valve support |
US5840081A (en) * | 1990-05-18 | 1998-11-24 | Andersen; Henning Rud | System and method for implanting cardiac valves |
US5843181A (en) * | 1994-04-18 | 1998-12-01 | Hancock Jaffe Laboratories | Biological material pre-fixation treatment |
US5851232A (en) * | 1997-03-15 | 1998-12-22 | Lois; William A. | Venous stent |
US5855601A (en) * | 1996-06-21 | 1999-01-05 | The Trustees Of Columbia University In The City Of New York | Artificial heart valve and method and device for implanting the same |
US5855602A (en) * | 1996-09-09 | 1999-01-05 | Shelhigh, Inc. | Heart valve prosthesis |
US5855597A (en) * | 1997-05-07 | 1999-01-05 | Iowa-India Investments Co. Limited | Stent valve and stent graft for percutaneous surgery |
US5861028A (en) * | 1996-09-09 | 1999-01-19 | Shelhigh Inc | Natural tissue heart valve and stent prosthesis and method for making the same |
US5876445A (en) * | 1991-10-09 | 1999-03-02 | Boston Scientific Corporation | Medical stents for body lumens exhibiting peristaltic motion |
US5910170A (en) * | 1997-12-17 | 1999-06-08 | St. Jude Medical, Inc. | Prosthetic heart valve stent utilizing mounting clips |
US5928281A (en) * | 1997-03-27 | 1999-07-27 | Baxter International Inc. | Tissue heart valves |
US5935163A (en) * | 1998-03-31 | 1999-08-10 | Shelhigh, Inc. | Natural tissue heart valve prosthesis |
US5938696A (en) * | 1994-02-09 | 1999-08-17 | Boston Scientific Technology, Inc. | Bifurcated endoluminal prosthesis |
US5957949A (en) * | 1997-05-01 | 1999-09-28 | World Medical Manufacturing Corp. | Percutaneous placement valve stent |
US6068638A (en) * | 1995-10-13 | 2000-05-30 | Transvascular, Inc. | Device, system and method for interstitial transvascular intervention |
US6071277A (en) * | 1996-03-05 | 2000-06-06 | Vnus Medical Technologies, Inc. | Method and apparatus for reducing the size of a hollow anatomical structure |
US6086610A (en) * | 1996-10-22 | 2000-07-11 | Nitinol Devices & Components | Composite self expanding stent device having a restraining element |
US6124523A (en) * | 1995-03-10 | 2000-09-26 | Impra, Inc. | Encapsulated stent |
US6158614A (en) * | 1997-07-30 | 2000-12-12 | Kimberly-Clark Worldwide, Inc. | Wet wipe dispenser with refill cartridge |
US6185216B1 (en) * | 1995-06-06 | 2001-02-06 | Marconi Communications Limited | Synchronization in an SDH network |
US6200336B1 (en) * | 1998-06-02 | 2001-03-13 | Cook Incorporated | Multiple-sided intraluminal medical device |
US6228112B1 (en) * | 1999-05-14 | 2001-05-08 | Jack Klootz | Artificial heart valve without a hinge |
US6245100B1 (en) * | 2000-02-01 | 2001-06-12 | Cordis Corporation | Method for making a self-expanding stent-graft |
US6245102B1 (en) * | 1997-05-07 | 2001-06-12 | Iowa-India Investments Company Ltd. | Stent, stent graft and stent valve |
US6283995B1 (en) * | 1999-04-15 | 2001-09-04 | Sulzer Carbomedics Inc. | Heart valve leaflet with scalloped free margin |
US6287334B1 (en) * | 1996-12-18 | 2001-09-11 | Venpro Corporation | Device for regulating the flow of blood through the blood system |
US6296662B1 (en) * | 1999-05-26 | 2001-10-02 | Sulzer Carbiomedics Inc. | Bioprosthetic heart valve with balanced stent post deflection |
US6299637B1 (en) * | 1999-08-20 | 2001-10-09 | Samuel M. Shaolian | Transluminally implantable venous valve |
US6309413B1 (en) * | 1993-10-21 | 2001-10-30 | Corvita Corporation | Expandable supportive endoluminal grafts |
US6315791B1 (en) * | 1996-12-03 | 2001-11-13 | Atrium Medical Corporation | Self-expanding prothesis |
US6355056B1 (en) * | 1995-06-01 | 2002-03-12 | Meadox Medicals, Inc. | Implantable intraluminal prosthesis |
US20020032481A1 (en) * | 2000-09-12 | 2002-03-14 | Shlomo Gabbay | Heart valve prosthesis and sutureless implantation of a heart valve prosthesis |
US6375787B1 (en) * | 1993-04-23 | 2002-04-23 | Schneider (Europe) Ag | Methods for applying a covering layer to a stent |
US6494909B2 (en) * | 2000-12-01 | 2002-12-17 | Prodesco, Inc. | Endovascular valve |
Family Cites Families (31)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US3548417A (en) * | 1967-09-05 | 1970-12-22 | Ronnie G Kischer | Heart valve having a flexible wall which rotates between open and closed positions |
US4604762A (en) * | 1981-02-13 | 1986-08-12 | Thoratec Laboratories Corporation | Arterial graft prosthesis |
US4726274A (en) * | 1986-01-10 | 1988-02-23 | Beniamino Pitoni | Mitering device |
IT215259Z2 (en) * | 1988-08-08 | 1990-09-11 | Marianna Calogero | EXPANDABLE PROSTHESIS FOR CORRECTIONS OF MYOPYSTROPHIES. |
JP3106252B2 (en) * | 1991-02-18 | 2000-11-06 | 株式会社ニフコ | Vehicle fuel tank device |
US5183953A (en) * | 1992-01-08 | 1993-02-02 | Anderson Manufacturing Company, Inc. | Flexible cover/guard for rifle and piston scopes having a resilient protective inner portion and a fabric outer portion secured thereto |
US5671433A (en) * | 1992-09-18 | 1997-09-23 | Vadem Corporation | Mappable functions from single chip/multi-chip processors for computers |
US5338570A (en) * | 1993-02-18 | 1994-08-16 | Westinghouse Electric Corp. | Method for finishing wood slatted articles of furniture |
US5554185A (en) * | 1994-07-18 | 1996-09-10 | Block; Peter C. | Inflatable prosthetic cardiovascular valve for percutaneous transluminal implantation of same |
US6451047B2 (en) * | 1995-03-10 | 2002-09-17 | Impra, Inc. | Encapsulated intraluminal stent-graft and methods of making same |
WO1997000651A1 (en) * | 1995-06-20 | 1997-01-09 | Agathos Efstathios A | Human valve replacement with marine mammal valve |
US5788626A (en) * | 1995-11-21 | 1998-08-04 | Schneider (Usa) Inc | Method of making a stent-graft covered with expanded polytetrafluoroethylene |
EP0836263B1 (en) * | 1996-03-13 | 2005-05-04 | Citizen Watch Co. Ltd. | Power supply for electronic timepiece |
DE69719237T2 (en) | 1996-05-23 | 2003-11-27 | Samsung Electronics Co Ltd | Flexible, self-expandable stent and method for its manufacture |
EP0850607A1 (en) * | 1996-12-31 | 1998-07-01 | Cordis Corporation | Valve prosthesis for implantation in body channels |
US6342067B1 (en) | 1998-01-09 | 2002-01-29 | Nitinol Development Corporation | Intravascular stent having curved bridges for connecting adjacent hoops |
US6488701B1 (en) * | 1998-03-31 | 2002-12-03 | Medtronic Ave, Inc. | Stent-graft assembly with thin-walled graft component and method of manufacture |
DE938879T1 (en) * | 1998-02-25 | 2000-04-20 | Medtronic Ave Inc N D Ges D St | Stent graft and manufacturing method therefor |
US6200338B1 (en) * | 1998-12-31 | 2001-03-13 | Ethicon, Inc. | Enhanced radiopacity of peripheral and central catheter tubing |
FR2788217A1 (en) * | 1999-01-12 | 2000-07-13 | Brice Letac | PROSTHETIC VALVE IMPLANTABLE BY CATHETERISM, OR SURGICAL |
US6425916B1 (en) * | 1999-02-10 | 2002-07-30 | Michi E. Garrison | Methods and devices for implanting cardiac valves |
AU3999700A (en) | 1999-02-12 | 2000-08-29 | Johns Hopkins University, The | Venous valve implant bioprosthesis and endovascular treatment for venous insufficiency |
US6440164B1 (en) * | 1999-10-21 | 2002-08-27 | Scimed Life Systems, Inc. | Implantable prosthetic valve |
US6458153B1 (en) * | 1999-12-31 | 2002-10-01 | Abps Venture One, Ltd. | Endoluminal cardiac and venous valve prostheses and methods of manufacture and delivery thereof |
US6355058B1 (en) * | 1999-12-30 | 2002-03-12 | Advanced Cardiovascular Systems, Inc. | Stent with radiopaque coating consisting of particles in a binder |
US6613082B2 (en) * | 2000-03-13 | 2003-09-02 | Jun Yang | Stent having cover with drug delivery capability |
US6746773B2 (en) * | 2000-09-29 | 2004-06-08 | Ethicon, Inc. | Coatings for medical devices |
CA2424029C (en) * | 2000-09-29 | 2008-01-29 | Cordis Corporation | Coated medical devices |
US6503272B2 (en) * | 2001-03-21 | 2003-01-07 | Cordis Corporation | Stent-based venous valves |
US6913625B2 (en) * | 2002-03-07 | 2005-07-05 | Scimed Life Systems, Inc. | Ureteral stent |
US7351256B2 (en) * | 2002-05-10 | 2008-04-01 | Cordis Corporation | Frame based unidirectional flow prosthetic implant |
-
2003
- 2003-05-06 AU AU2003225291A patent/AU2003225291A1/en not_active Abandoned
- 2003-05-06 EP EP08075133A patent/EP2149350A3/en not_active Withdrawn
- 2003-05-06 US US10/430,113 patent/US20030225447A1/en not_active Abandoned
- 2003-05-06 MX MXPA04011144A patent/MXPA04011144A/en unknown
- 2003-05-06 JP JP2004502885A patent/JP2005525169A/en active Pending
- 2003-05-06 CA CA002485285A patent/CA2485285A1/en not_active Abandoned
- 2003-05-06 WO PCT/US2003/014009 patent/WO2003094795A1/en active Application Filing
- 2003-05-06 EP EP03722012A patent/EP1507492A1/en not_active Withdrawn
- 2003-05-08 DE DE60332938T patent/DE60332938D1/en not_active Expired - Lifetime
- 2003-05-08 EP EP03724532A patent/EP1509171B1/en not_active Revoked
- 2003-05-08 AT AT03724532T patent/ATE470406T1/en not_active IP Right Cessation
- 2003-05-08 WO PCT/US2003/014530 patent/WO2003094799A1/en active Application Filing
- 2003-05-08 JP JP2004502889A patent/JP2005525172A/en active Pending
- 2003-05-08 AU AU2003230363A patent/AU2003230363A1/en not_active Abandoned
- 2003-05-08 MX MXPA04011147A patent/MXPA04011147A/en active IP Right Grant
- 2003-05-08 CA CA002485293A patent/CA2485293A1/en not_active Abandoned
- 2003-05-08 US US10/431,967 patent/US20030236568A1/en not_active Abandoned
- 2003-05-09 US US10/434,891 patent/US7758632B2/en active Active
- 2003-05-09 AU AU2003298515A patent/AU2003298515A1/en not_active Abandoned
- 2003-05-09 WO PCT/US2003/015323 patent/WO2004034933A2/en not_active Application Discontinuation
- 2003-05-09 MX MXPA04011148A patent/MXPA04011148A/en active IP Right Grant
- 2003-05-09 EP EP03796268.5A patent/EP1667604B1/en not_active Expired - Lifetime
- 2003-05-09 CA CA2501712A patent/CA2501712C/en not_active Expired - Lifetime
-
2009
- 2009-01-19 AU AU2009200209A patent/AU2009200209B2/en not_active Expired
- 2009-01-19 AU AU2009200210A patent/AU2009200210A1/en not_active Abandoned
Patent Citations (75)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US554185A (en) * | 1896-02-04 | George m | ||
US4323525A (en) * | 1978-04-19 | 1982-04-06 | Imperial Chemical Industries Limited | Electrostatic spinning of tubular products |
US4892541A (en) * | 1982-11-29 | 1990-01-09 | Tascon Medical Technology Corporation | Heart valve prosthesis |
US4692164A (en) * | 1986-03-06 | 1987-09-08 | Moskovskoe Vysshee Tekhnicheskoe Uchilische, Imeni N.E. Baumana | Bioprosthetic heart valve, methods and device for preparation thereof |
US4790843A (en) * | 1986-06-16 | 1988-12-13 | Baxter Travenol Laboratories, Inc. | Prosthetic heart valve assembly |
US4725274A (en) * | 1986-10-24 | 1988-02-16 | Baxter Travenol Laboratories, Inc. | Prosthetic heart valve |
US4851000A (en) * | 1987-07-31 | 1989-07-25 | Pacific Biomedical Holdings, Ltd. | Bioprosthetic valve stent |
US5156621A (en) * | 1988-03-22 | 1992-10-20 | Navia Jose A | Stentless bioprosthetic cardiac valve |
US5032128A (en) * | 1988-07-07 | 1991-07-16 | Medtronic, Inc. | Heart valve prosthesis |
US4969896A (en) * | 1989-02-01 | 1990-11-13 | Interpore International | Vascular graft prosthesis and method of making the same |
US5500014A (en) * | 1989-05-31 | 1996-03-19 | Baxter International Inc. | Biological valvular prothesis |
US5824061A (en) * | 1989-05-31 | 1998-10-20 | Baxter International Inc. | Vascular and venous valve implant prostheses |
US5997573A (en) * | 1989-05-31 | 1999-12-07 | Baxter International, Inc. | Stent devices and support/restrictor assemblies for use in conjunction with prosthetic vascular grafts |
US5609626A (en) * | 1989-05-31 | 1997-03-11 | Baxter International Inc. | Stent devices and support/restrictor assemblies for use in conjunction with prosthetic vascular grafts |
US5037434A (en) * | 1990-04-11 | 1991-08-06 | Carbomedics, Inc. | Bioprosthetic heart valve with elastic commissures |
US5147391A (en) * | 1990-04-11 | 1992-09-15 | Carbomedics, Inc. | Bioprosthetic heart valve with semi-permeable commissure posts and deformable leaflets |
US5411552A (en) * | 1990-05-18 | 1995-05-02 | Andersen; Henning R. | Valve prothesis for implantation in the body and a catheter for implanting such valve prothesis |
US5840081A (en) * | 1990-05-18 | 1998-11-24 | Andersen; Henning Rud | System and method for implanting cardiac valves |
US5415667A (en) * | 1990-06-07 | 1995-05-16 | Frater; Robert W. M. | Mitral heart valve replacements |
US5326371A (en) * | 1991-01-24 | 1994-07-05 | Autogenics | Rapid assembly, concentric mating stent, tissue heart valve with enhanced clamping and tissue alignment |
US5423887A (en) * | 1991-01-24 | 1995-06-13 | Autogenics | Rapid assembly, concentric mating stent, tissue heart valve with enhanced clamping and tissue alignment |
US5326370A (en) * | 1991-01-24 | 1994-07-05 | Autogenics | Prefabricated sterile and disposable kits for the rapid assembly of a tissue heart valve |
US5163955A (en) * | 1991-01-24 | 1992-11-17 | Autogenics | Rapid assembly, concentric mating stent, tissue heart valve with enhanced clamping and tissue alignment |
US5489298A (en) * | 1991-01-24 | 1996-02-06 | Autogenics | Rapid assembly concentric mating stent, tissue heart valve with enhanced clamping and tissue exposure |
US5449385A (en) * | 1991-05-08 | 1995-09-12 | Nika Health Products Limited | Support for a heart valve prosthesis |
US5344442A (en) * | 1991-05-16 | 1994-09-06 | Mures Cardiovasular Research, Inc. | Cardiac valve |
US5358518A (en) * | 1991-06-25 | 1994-10-25 | Sante Camilli | Artificial venous valve |
US5662713A (en) * | 1991-10-09 | 1997-09-02 | Boston Scientific Corporation | Medical stents for body lumens exhibiting peristaltic motion |
US5876445A (en) * | 1991-10-09 | 1999-03-02 | Boston Scientific Corporation | Medical stents for body lumens exhibiting peristaltic motion |
US5123919A (en) * | 1991-11-21 | 1992-06-23 | Carbomedics, Inc. | Combined prosthetic aortic heart valve and vascular graft |
US5163953A (en) * | 1992-02-10 | 1992-11-17 | Vince Dennis J | Toroidal artificial heart valve stent |
US5469868A (en) * | 1992-02-12 | 1995-11-28 | Reger Medical Inc. | Method of making an artificial heart valve stent |
US5258023A (en) * | 1992-02-12 | 1993-11-02 | Reger Medical Development, Inc. | Prosthetic heart valve |
US5449384A (en) * | 1992-09-28 | 1995-09-12 | Medtronic, Inc. | Dynamic annulus heart valve employing preserved porcine valve leaflets |
US5607463A (en) * | 1993-03-30 | 1997-03-04 | Medtronic, Inc. | Intravascular medical device |
US6375787B1 (en) * | 1993-04-23 | 2002-04-23 | Schneider (Europe) Ag | Methods for applying a covering layer to a stent |
US5549665A (en) * | 1993-06-18 | 1996-08-27 | London Health Association | Bioprostethic valve |
US6309413B1 (en) * | 1993-10-21 | 2001-10-30 | Corvita Corporation | Expandable supportive endoluminal grafts |
US5480424A (en) * | 1993-11-01 | 1996-01-02 | Cox; James L. | Heart valve replacement using flexible tubes |
US5607465A (en) * | 1993-12-14 | 1997-03-04 | Camilli; Sante | Percutaneous implantable valve for the use in blood vessels |
US5612885A (en) * | 1993-12-17 | 1997-03-18 | Autogenics | Method for constructing a heart valve stent |
US5938696A (en) * | 1994-02-09 | 1999-08-17 | Boston Scientific Technology, Inc. | Bifurcated endoluminal prosthesis |
US5843181A (en) * | 1994-04-18 | 1998-12-01 | Hancock Jaffe Laboratories | Biological material pre-fixation treatment |
US5697382A (en) * | 1994-05-05 | 1997-12-16 | Autogenics | Heart valve assembly method |
US5695499A (en) * | 1994-10-27 | 1997-12-09 | Schneider (Usa) Inc. | Medical device supported by spirally wound wire |
US5562729A (en) * | 1994-11-01 | 1996-10-08 | Biocontrol Technology, Inc. | Heart valve |
US6124523A (en) * | 1995-03-10 | 2000-09-26 | Impra, Inc. | Encapsulated stent |
US6355056B1 (en) * | 1995-06-01 | 2002-03-12 | Meadox Medicals, Inc. | Implantable intraluminal prosthesis |
US6185216B1 (en) * | 1995-06-06 | 2001-02-06 | Marconi Communications Limited | Synchronization in an SDH network |
US5728152A (en) * | 1995-06-07 | 1998-03-17 | St. Jude Medical, Inc. | Bioresorbable heart valve support |
US5895420A (en) * | 1995-06-07 | 1999-04-20 | St. Jude Medical, Inc. | Bioresorbable heart valve support |
US6068638A (en) * | 1995-10-13 | 2000-05-30 | Transvascular, Inc. | Device, system and method for interstitial transvascular intervention |
US6071277A (en) * | 1996-03-05 | 2000-06-06 | Vnus Medical Technologies, Inc. | Method and apparatus for reducing the size of a hollow anatomical structure |
US5855601A (en) * | 1996-06-21 | 1999-01-05 | The Trustees Of Columbia University In The City Of New York | Artificial heart valve and method and device for implanting the same |
US5855602A (en) * | 1996-09-09 | 1999-01-05 | Shelhigh, Inc. | Heart valve prosthesis |
US5861028A (en) * | 1996-09-09 | 1999-01-19 | Shelhigh Inc | Natural tissue heart valve and stent prosthesis and method for making the same |
US6086610A (en) * | 1996-10-22 | 2000-07-11 | Nitinol Devices & Components | Composite self expanding stent device having a restraining element |
US6315791B1 (en) * | 1996-12-03 | 2001-11-13 | Atrium Medical Corporation | Self-expanding prothesis |
US6287334B1 (en) * | 1996-12-18 | 2001-09-11 | Venpro Corporation | Device for regulating the flow of blood through the blood system |
US5851232A (en) * | 1997-03-15 | 1998-12-22 | Lois; William A. | Venous stent |
US5928281A (en) * | 1997-03-27 | 1999-07-27 | Baxter International Inc. | Tissue heart valves |
US5957949A (en) * | 1997-05-01 | 1999-09-28 | World Medical Manufacturing Corp. | Percutaneous placement valve stent |
US6245102B1 (en) * | 1997-05-07 | 2001-06-12 | Iowa-India Investments Company Ltd. | Stent, stent graft and stent valve |
US5855597A (en) * | 1997-05-07 | 1999-01-05 | Iowa-India Investments Co. Limited | Stent valve and stent graft for percutaneous surgery |
US6158614A (en) * | 1997-07-30 | 2000-12-12 | Kimberly-Clark Worldwide, Inc. | Wet wipe dispenser with refill cartridge |
US5910170A (en) * | 1997-12-17 | 1999-06-08 | St. Jude Medical, Inc. | Prosthetic heart valve stent utilizing mounting clips |
US5935163A (en) * | 1998-03-31 | 1999-08-10 | Shelhigh, Inc. | Natural tissue heart valve prosthesis |
US6200336B1 (en) * | 1998-06-02 | 2001-03-13 | Cook Incorporated | Multiple-sided intraluminal medical device |
US6283995B1 (en) * | 1999-04-15 | 2001-09-04 | Sulzer Carbomedics Inc. | Heart valve leaflet with scalloped free margin |
US6228112B1 (en) * | 1999-05-14 | 2001-05-08 | Jack Klootz | Artificial heart valve without a hinge |
US6296662B1 (en) * | 1999-05-26 | 2001-10-02 | Sulzer Carbiomedics Inc. | Bioprosthetic heart valve with balanced stent post deflection |
US6299637B1 (en) * | 1999-08-20 | 2001-10-09 | Samuel M. Shaolian | Transluminally implantable venous valve |
US6245100B1 (en) * | 2000-02-01 | 2001-06-12 | Cordis Corporation | Method for making a self-expanding stent-graft |
US20020032481A1 (en) * | 2000-09-12 | 2002-03-14 | Shlomo Gabbay | Heart valve prosthesis and sutureless implantation of a heart valve prosthesis |
US6494909B2 (en) * | 2000-12-01 | 2002-12-17 | Prodesco, Inc. | Endovascular valve |
Cited By (352)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20130226291A1 (en) * | 1999-06-02 | 2013-08-29 | Dusan Pavcnik | Implantable vascular device |
US9078746B2 (en) * | 1999-06-02 | 2015-07-14 | Cook Medical Technologies Llc | Implantable vascular device |
US6840957B2 (en) * | 1999-10-21 | 2005-01-11 | Scimed Life Systems, Inc. | Implantable prosthetic valve |
US20040098112A1 (en) * | 1999-10-21 | 2004-05-20 | Scimed Life Systems, Inc. | Implantable prosthetic valve |
US20050143807A1 (en) * | 2000-02-03 | 2005-06-30 | Dusan Pavcnik | Implantable vascular device comprising a bioabsorbable frame |
US9439762B2 (en) | 2000-06-01 | 2016-09-13 | Edwards Lifesciences Corporation | Methods of implant of a heart valve with a convertible sewing ring |
US10238486B2 (en) | 2000-06-01 | 2019-03-26 | Edwards Lifesciences Corporation | Heart valve with integrated stent and sewing ring |
US7819915B2 (en) | 2000-07-27 | 2010-10-26 | Edwards Lifesciences Corporation | Heart valve holders and handling clips therefor |
US7776053B2 (en) | 2000-10-26 | 2010-08-17 | Boston Scientific Scimed, Inc. | Implantable valve system |
US8038708B2 (en) | 2001-02-05 | 2011-10-18 | Cook Medical Technologies Llc | Implantable device with remodelable material and covering material |
US8628570B2 (en) * | 2001-07-04 | 2014-01-14 | Medtronic Corevalve Llc | Assembly for placing a prosthetic valve in a duct in the body |
US9149357B2 (en) | 2001-07-04 | 2015-10-06 | Medtronic CV Luxembourg S.a.r.l. | Heart valve assemblies |
US20110301692A1 (en) * | 2001-07-04 | 2011-12-08 | Medtronic Corevalve Llc | Assembly for Placing a Prosthetic Valve in a Duct in the Body |
US7972377B2 (en) | 2001-12-27 | 2011-07-05 | Medtronic, Inc. | Bioprosthetic heart valve |
US7007698B2 (en) | 2002-04-03 | 2006-03-07 | Boston Scientific Corporation | Body lumen closure |
US7682385B2 (en) | 2002-04-03 | 2010-03-23 | Boston Scientific Corporation | Artificial valve |
US8349003B2 (en) | 2002-07-16 | 2013-01-08 | Medtronic, Inc. | Suture locking assembly and method of use |
US7959674B2 (en) | 2002-07-16 | 2011-06-14 | Medtronic, Inc. | Suture locking assembly and method of use |
US8551162B2 (en) | 2002-12-20 | 2013-10-08 | Medtronic, Inc. | Biologically implantable prosthesis |
US8460373B2 (en) | 2002-12-20 | 2013-06-11 | Medtronic, Inc. | Method for implanting a heart valve within an annulus of a patient |
US9333078B2 (en) | 2002-12-20 | 2016-05-10 | Medtronic, Inc. | Heart valve assemblies |
US10595991B2 (en) | 2002-12-20 | 2020-03-24 | Medtronic, Inc. | Heart valve assemblies |
US8025695B2 (en) | 2002-12-20 | 2011-09-27 | Medtronic, Inc. | Biologically implantable heart valve system |
US7981153B2 (en) | 2002-12-20 | 2011-07-19 | Medtronic, Inc. | Biologically implantable prosthesis methods of using |
US8623080B2 (en) | 2002-12-20 | 2014-01-07 | Medtronic, Inc. | Biologically implantable prosthesis and methods of using the same |
US7780627B2 (en) | 2002-12-30 | 2010-08-24 | Boston Scientific Scimed, Inc. | Valve treatment catheter and methods |
US6945957B2 (en) | 2002-12-30 | 2005-09-20 | Scimed Life Systems, Inc. | Valve treatment catheter and methods |
US20060212110A1 (en) * | 2003-03-17 | 2006-09-21 | Osborne Thomas A | Vascular valve with removable support component |
US7524332B2 (en) * | 2003-03-17 | 2009-04-28 | Cook Incorporated | Vascular valve with removable support component |
US20100030314A1 (en) * | 2003-04-08 | 2010-02-04 | Case Brian C | Implantable support device with graft |
US7670366B2 (en) | 2003-04-08 | 2010-03-02 | Cook Incorporated | Intraluminal support device with graft |
US20040225348A1 (en) * | 2003-04-08 | 2004-11-11 | Case Brian C. | Intraluminal support device with graft |
US8771338B2 (en) | 2003-04-24 | 2014-07-08 | Cook Medical Technologies Llc | Intralumenally-implantable frames |
US8221492B2 (en) | 2003-04-24 | 2012-07-17 | Cook Medical Technologies | Artificial valve prosthesis with improved flow dynamics |
US9421096B2 (en) | 2003-04-24 | 2016-08-23 | Cook Medical Technologies Llc | Artificial valve prosthesis with improved flow dynamics |
US9326871B2 (en) | 2003-04-24 | 2016-05-03 | Cook Medical Technologies Llc | Intralumenally-implantable frames |
US7658759B2 (en) * | 2003-04-24 | 2010-02-09 | Cook Incorporated | Intralumenally implantable frames |
US8470020B2 (en) | 2003-04-24 | 2013-06-25 | Cook Medical Technologies Llc | Intralumenally-implantable frames |
US8157857B2 (en) | 2003-04-24 | 2012-04-17 | Cook Medical Technologies Llc | Intralumenally-implantable frames |
US20070260327A1 (en) * | 2003-04-24 | 2007-11-08 | Case Brian C | Artificial Valve Prosthesis with Improved Flow Dynamics |
US20100131055A1 (en) * | 2003-04-24 | 2010-05-27 | Cook Incorporated | Artificial valve prosthesis with improved flow dynamics |
US20100114296A1 (en) * | 2003-04-24 | 2010-05-06 | Cook Incorporated | Intralumenally-implantable frames |
US7442204B2 (en) * | 2003-07-08 | 2008-10-28 | Ventor Technologies, Ltd. | Fluid flow prosthetic device |
US20070185565A1 (en) * | 2003-07-08 | 2007-08-09 | Ventor Technologies Ltd. | Fluid flow prosthetic device |
US7429269B2 (en) * | 2003-07-08 | 2008-09-30 | Ventor Technologies Ltd. | Aortic prosthetic devices |
US20060259134A1 (en) * | 2003-07-08 | 2006-11-16 | Ehud Schwammenthal | Implantable prosthetic devices particularly for transarterial delivery in the treatment of aortic stenosis, and methods of implanting such devices |
US8021421B2 (en) | 2003-08-22 | 2011-09-20 | Medtronic, Inc. | Prosthesis heart valve fixturing device |
US8747463B2 (en) | 2003-08-22 | 2014-06-10 | Medtronic, Inc. | Methods of using a prosthesis fixturing device |
US9579194B2 (en) | 2003-10-06 | 2017-02-28 | Medtronic ATS Medical, Inc. | Anchoring structure with concave landing zone |
US20060259137A1 (en) * | 2003-10-06 | 2006-11-16 | Jason Artof | Minimally invasive valve replacement system |
US8603161B2 (en) | 2003-10-08 | 2013-12-10 | Medtronic, Inc. | Attachment device and methods of using the same |
US10869764B2 (en) | 2003-12-19 | 2020-12-22 | Boston Scientific Scimed, Inc. | Venous valve apparatus, system, and method |
US7854761B2 (en) | 2003-12-19 | 2010-12-21 | Boston Scientific Scimed, Inc. | Methods for venous valve replacement with a catheter |
US8128681B2 (en) | 2003-12-19 | 2012-03-06 | Boston Scientific Scimed, Inc. | Venous valve apparatus, system, and method |
US9301843B2 (en) | 2003-12-19 | 2016-04-05 | Boston Scientific Scimed, Inc. | Venous valve apparatus, system, and method |
US8721717B2 (en) | 2003-12-19 | 2014-05-13 | Boston Scientific Scimed, Inc. | Venous valve apparatus, system, and method |
US9730794B2 (en) | 2004-01-23 | 2017-08-15 | Edwards Lifesciences Corporation | Prosthetic mitral valve |
US9155617B2 (en) | 2004-01-23 | 2015-10-13 | Edwards Lifesciences Corporation | Prosthetic mitral valve |
US10342661B2 (en) | 2004-01-23 | 2019-07-09 | Edwards Lifesciences Corporation | Prosthetic mitral valve |
US10085836B2 (en) | 2004-01-23 | 2018-10-02 | Edwards Lifesciences Corporation | Prosthetic mitral valve |
US8337545B2 (en) | 2004-02-09 | 2012-12-25 | Cook Medical Technologies Llc | Woven implantable device |
US9066798B2 (en) | 2004-02-09 | 2015-06-30 | Cook Medical Technologies Llc | Woven implantable device |
US8216299B2 (en) | 2004-04-01 | 2012-07-10 | Cook Medical Technologies Llc | Method to retract a body vessel wall with remodelable material |
EP2450008A2 (en) * | 2004-09-02 | 2012-05-09 | Boston Scientific Scimed, Inc. | Cardiac valve |
EP2450008A3 (en) * | 2004-09-02 | 2013-08-21 | Boston Scientific Scimed, Inc. | Cardiac valve |
WO2006031469A1 (en) * | 2004-09-02 | 2006-03-23 | Boston Scientific Limited | Cardiac valve, system, and method |
US9918834B2 (en) | 2004-09-02 | 2018-03-20 | Boston Scientific Scimed, Inc. | Cardiac valve, system and method |
US8932349B2 (en) * | 2004-09-02 | 2015-01-13 | Boston Scientific Scimed, Inc. | Cardiac valve, system, and method |
US8002824B2 (en) | 2004-09-02 | 2011-08-23 | Boston Scientific Scimed, Inc. | Cardiac valve, system, and method |
US20110301705A1 (en) * | 2004-09-02 | 2011-12-08 | Boston Scientific Scimed, Inc. | Cardiac Valve, System, and Method |
US7566343B2 (en) * | 2004-09-02 | 2009-07-28 | Boston Scientific Scimed, Inc. | Cardiac valve, system, and method |
US20100114300A1 (en) * | 2004-12-01 | 2010-05-06 | Cook Incorporated | Medical device with leak path |
US20090216311A1 (en) * | 2004-12-20 | 2009-08-27 | Jacob Flagle | Intraluminal support frame |
US20060173532A1 (en) * | 2004-12-20 | 2006-08-03 | Jacob Flagle | Intraluminal support frame and medical devices including the support frame |
US8123794B2 (en) | 2004-12-20 | 2012-02-28 | Cook Medical Technologies Llc | Intraluminal support frame |
US7544205B2 (en) | 2004-12-20 | 2009-06-09 | Cook Incorporated | Intraluminal support frame and medical devices including the support frame |
US11517431B2 (en) | 2005-01-20 | 2022-12-06 | Jenavalve Technology, Inc. | Catheter system for implantation of prosthetic heart valves |
US9622859B2 (en) | 2005-02-01 | 2017-04-18 | Boston Scientific Scimed, Inc. | Filter system and method |
US7854755B2 (en) | 2005-02-01 | 2010-12-21 | Boston Scientific Scimed, Inc. | Vascular catheter, system, and method |
US7878966B2 (en) | 2005-02-04 | 2011-02-01 | Boston Scientific Scimed, Inc. | Ventricular assist and support device |
US7670368B2 (en) | 2005-02-07 | 2010-03-02 | Boston Scientific Scimed, Inc. | Venous valve apparatus, system, and method |
US7780722B2 (en) | 2005-02-07 | 2010-08-24 | Boston Scientific Scimed, Inc. | Venous valve apparatus, system, and method |
US8574257B2 (en) | 2005-02-10 | 2013-11-05 | Edwards Lifesciences Corporation | System, device, and method for providing access in a cardiovascular environment |
US9370419B2 (en) | 2005-02-23 | 2016-06-21 | Boston Scientific Scimed, Inc. | Valve apparatus, system and method |
US9808341B2 (en) | 2005-02-23 | 2017-11-07 | Boston Scientific Scimed Inc. | Valve apparatus, system and method |
US7867274B2 (en) | 2005-02-23 | 2011-01-11 | Boston Scientific Scimed, Inc. | Valve apparatus, system and method |
US8500802B2 (en) | 2005-04-08 | 2013-08-06 | Medtronic, Inc. | Two-piece prosthetic valves with snap-in connection and methods for use |
US7951197B2 (en) | 2005-04-08 | 2011-05-31 | Medtronic, Inc. | Two-piece prosthetic valves with snap-in connection and methods for use |
US7722666B2 (en) | 2005-04-15 | 2010-05-25 | Boston Scientific Scimed, Inc. | Valve apparatus, system and method |
US9861473B2 (en) | 2005-04-15 | 2018-01-09 | Boston Scientific Scimed Inc. | Valve apparatus, system and method |
WO2006113496A3 (en) * | 2005-04-15 | 2007-01-04 | Boston Scient Scimed Inc | Valve apparatus, system and method |
WO2006113496A2 (en) * | 2005-04-15 | 2006-10-26 | Boston Scientific Limited | Valve apparatus, system and method |
US8512399B2 (en) | 2005-04-15 | 2013-08-20 | Boston Scientific Scimed, Inc. | Valve apparatus, system and method |
USD812226S1 (en) | 2005-05-13 | 2018-03-06 | Medtronic Corevalve Llc | Heart valve prosthesis |
USD732666S1 (en) | 2005-05-13 | 2015-06-23 | Medtronic Corevalve, Inc. | Heart valve prosthesis |
US20090088828A1 (en) * | 2005-05-17 | 2009-04-02 | Nicast Ltd. | Electrically Charged Implantable Medical Device |
WO2006123340A3 (en) * | 2005-05-17 | 2007-03-29 | Nicast Ltd | Electrically charged implantable medical device |
US11284998B2 (en) | 2005-05-24 | 2022-03-29 | Edwards Lifesciences Corporation | Surgical methods of replacing prosthetic heart valves |
US9554903B2 (en) | 2005-05-24 | 2017-01-31 | Edwards Lifesciences Corporation | Rapid deployment prosthetic heart valve |
US7708775B2 (en) | 2005-05-24 | 2010-05-04 | Edwards Lifesciences Corporation | Methods for rapid deployment of prosthetic heart valves |
US8911493B2 (en) | 2005-05-24 | 2014-12-16 | Edwards Lifesciences Corporation | Rapid deployment prosthetic heart valves |
US10130468B2 (en) | 2005-05-24 | 2018-11-20 | Edwards Lifesciences Corporation | Replacement prosthetic heart valves |
US8500798B2 (en) | 2005-05-24 | 2013-08-06 | Edwards Lifesciences Corporation | Rapid deployment prosthetic heart valve |
US10456251B2 (en) | 2005-05-24 | 2019-10-29 | Edwards Lifesciences Corporation | Surgical methods of replacing prosthetic heart valves |
US8211169B2 (en) | 2005-05-27 | 2012-07-03 | Medtronic, Inc. | Gasket with collar for prosthetic heart valves and methods for using them |
US11337812B2 (en) | 2005-06-10 | 2022-05-24 | Boston Scientific Scimed, Inc. | Venous valve, system and method |
US9028542B2 (en) | 2005-06-10 | 2015-05-12 | Boston Scientific Scimed, Inc. | Venous valve, system, and method |
US8012198B2 (en) | 2005-06-10 | 2011-09-06 | Boston Scientific Scimed, Inc. | Venous valve, system, and method |
US8506625B2 (en) | 2005-07-13 | 2013-08-13 | Edwards Lifesciences Corporation | Contoured sewing ring for a prosthetic mitral heart valve |
US9474609B2 (en) | 2005-09-21 | 2016-10-25 | Boston Scientific Scimed, Inc. | Venous valve, system, and method with sinus pocket |
US10548734B2 (en) | 2005-09-21 | 2020-02-04 | Boston Scientific Scimed, Inc. | Venous valve, system, and method with sinus pocket |
US7951189B2 (en) | 2005-09-21 | 2011-05-31 | Boston Scientific Scimed, Inc. | Venous valve, system, and method with sinus pocket |
US8460365B2 (en) | 2005-09-21 | 2013-06-11 | Boston Scientific Scimed, Inc. | Venous valve, system, and method with sinus pocket |
US8672997B2 (en) | 2005-09-21 | 2014-03-18 | Boston Scientific Scimed, Inc. | Valve with sinus |
US7799038B2 (en) | 2006-01-20 | 2010-09-21 | Boston Scientific Scimed, Inc. | Translumenal apparatus, system, and method |
US7967857B2 (en) | 2006-01-27 | 2011-06-28 | Medtronic, Inc. | Gasket with spring collar for prosthetic heart valves and methods for making and using them |
US8821569B2 (en) | 2006-04-29 | 2014-09-02 | Medtronic, Inc. | Multiple component prosthetic heart valve assemblies and methods for delivering them |
US8021161B2 (en) | 2006-05-01 | 2011-09-20 | Edwards Lifesciences Corporation | Simulated heart valve root for training and testing |
US20070288087A1 (en) * | 2006-05-30 | 2007-12-13 | Cook Incorporated | Artificial valve prosthesis |
US8038710B2 (en) * | 2006-05-30 | 2011-10-18 | Cook Medical Technologies Llc | Artificial valve prosthesis |
EP2040645B1 (en) | 2006-07-17 | 2021-09-29 | 3F Therapeutics, Inc | Minimally invasive valve replacement system |
EP2040645A4 (en) * | 2006-07-17 | 2011-05-25 | 3F Therapeutics Inc | Minimally invasive valve replacement system |
EP2040645A1 (en) * | 2006-07-17 | 2009-04-01 | 3F Therapeutics, Inc | Minimally invasive valve replacement system |
WO2008010817A1 (en) * | 2006-07-17 | 2008-01-24 | 3F Therapeutics, Inc. | Minimally invasive valve replacement system |
US20080039952A1 (en) * | 2006-08-09 | 2008-02-14 | Coherex Medical, Inc. | Devices for reducing the size of an internal tissue opening |
US9138208B2 (en) * | 2006-08-09 | 2015-09-22 | Coherex Medical, Inc. | Devices for reducing the size of an internal tissue opening |
US9220487B2 (en) | 2006-08-09 | 2015-12-29 | Coherex Medical, Inc. | Devices for reducing the size of an internal tissue opening |
US8348996B2 (en) | 2006-09-19 | 2013-01-08 | Medtronic Ventor Technologies Ltd. | Valve prosthesis implantation techniques |
US8052750B2 (en) | 2006-09-19 | 2011-11-08 | Medtronic Ventor Technologies Ltd | Valve prosthesis fixation techniques using sandwiching |
US8876895B2 (en) | 2006-09-19 | 2014-11-04 | Medtronic Ventor Technologies Ltd. | Valve fixation member having engagement arms |
US8876894B2 (en) | 2006-09-19 | 2014-11-04 | Medtronic Ventor Technologies Ltd. | Leaflet-sensitive valve fixation member |
US8834564B2 (en) | 2006-09-19 | 2014-09-16 | Medtronic, Inc. | Sinus-engaging valve fixation member |
US11304801B2 (en) | 2006-09-19 | 2022-04-19 | Medtronic Ventor Technologies Ltd. | Sinus-engaging valve fixation member |
US11304802B2 (en) | 2006-09-19 | 2022-04-19 | Medtronic Ventor Technologies Ltd. | Sinus-engaging valve fixation member |
US20080071361A1 (en) * | 2006-09-19 | 2008-03-20 | Yosi Tuval | Leaflet-sensitive valve fixation member |
US8771345B2 (en) | 2006-09-19 | 2014-07-08 | Medtronic Ventor Technologies Ltd. | Valve prosthesis fixation techniques using sandwiching |
US8414643B2 (en) | 2006-09-19 | 2013-04-09 | Medtronic Ventor Technologies Ltd. | Sinus-engaging valve fixation member |
US9642704B2 (en) | 2006-09-19 | 2017-05-09 | Medtronic Ventor Technologies Ltd. | Catheter for implanting a valve prosthesis |
US8771346B2 (en) | 2006-09-19 | 2014-07-08 | Medtronic Ventor Technologies Ltd. | Valve prosthetic fixation techniques using sandwiching |
US8747460B2 (en) | 2006-09-19 | 2014-06-10 | Medtronic Ventor Technologies Ltd. | Methods for implanting a valve prothesis |
US11304800B2 (en) | 2006-09-19 | 2022-04-19 | Medtronic Ventor Technologies Ltd. | Sinus-engaging valve fixation member |
US20080071366A1 (en) * | 2006-09-19 | 2008-03-20 | Yosi Tuval | Axial-force fixation member for valve |
US10004601B2 (en) | 2006-09-19 | 2018-06-26 | Medtronic Ventor Technologies Ltd. | Valve prosthesis fixation techniques using sandwiching |
US20080071369A1 (en) * | 2006-09-19 | 2008-03-20 | Yosi Tuval | Valve fixation member having engagement arms |
US9138312B2 (en) | 2006-09-19 | 2015-09-22 | Medtronic Ventor Technologies Ltd. | Valve prostheses |
US8348995B2 (en) | 2006-09-19 | 2013-01-08 | Medtronic Ventor Technologies, Ltd. | Axial-force fixation member for valve |
US8133270B2 (en) | 2007-01-08 | 2012-03-13 | California Institute Of Technology | In-situ formation of a valve |
US8348999B2 (en) | 2007-01-08 | 2013-01-08 | California Institute Of Technology | In-situ formation of a valve |
US11504239B2 (en) | 2007-02-05 | 2022-11-22 | Boston Scientific Scimed, Inc. | Percutaneous valve, system and method |
US7967853B2 (en) | 2007-02-05 | 2011-06-28 | Boston Scientific Scimed, Inc. | Percutaneous valve, system and method |
US10226344B2 (en) | 2007-02-05 | 2019-03-12 | Boston Scientific Scimed, Inc. | Percutaneous valve, system and method |
US9421083B2 (en) | 2007-02-05 | 2016-08-23 | Boston Scientific Scimed Inc. | Percutaneous valve, system and method |
US8470023B2 (en) | 2007-02-05 | 2013-06-25 | Boston Scientific Scimed, Inc. | Percutaneous valve, system, and method |
US11357624B2 (en) | 2007-04-13 | 2022-06-14 | Jenavalve Technology, Inc. | Medical device for treating a heart valve insufficiency |
US20220096225A1 (en) * | 2007-06-04 | 2022-03-31 | St. Jude Medical, Llc | Prosthetic Heart Valves |
US11737870B2 (en) * | 2007-06-04 | 2023-08-29 | St. Jude Medical, Llc | Prosthetic heart valves |
US20090012596A1 (en) * | 2007-07-06 | 2009-01-08 | Boston Scientific Scimed, Inc. | Stent with Bioabsorbable Membrane |
US7637940B2 (en) | 2007-07-06 | 2009-12-29 | Boston Scientific Scimed, Inc. | Stent with bioabsorbable membrane |
US8828079B2 (en) | 2007-07-26 | 2014-09-09 | Boston Scientific Scimed, Inc. | Circulatory valve, system and method |
US9308360B2 (en) | 2007-08-23 | 2016-04-12 | Direct Flow Medical, Inc. | Translumenally implantable heart valve with formed in place support |
US10130463B2 (en) | 2007-08-23 | 2018-11-20 | Dfm, Llc | Translumenally implantable heart valve with formed in place support |
US11007053B2 (en) | 2007-09-26 | 2021-05-18 | St. Jude Medical, Llc | Collapsible prosthetic heart valves |
US11903823B2 (en) | 2007-09-26 | 2024-02-20 | St. Jude Medical, Llc | Collapsible prosthetic heart valves |
US9693859B2 (en) | 2007-09-26 | 2017-07-04 | St. Jude Medical, Llc | Collapsible prosthetic heart valves |
US9636221B2 (en) | 2007-09-26 | 2017-05-02 | St. Jude Medical, Inc. | Collapsible prosthetic heart valves |
US10292813B2 (en) | 2007-09-26 | 2019-05-21 | St. Jude Medical, Llc | Collapsible prosthetic heart valves |
US9820851B2 (en) | 2007-09-28 | 2017-11-21 | St. Jude Medical, Llc | Collapsible-expandable prosthetic heart valves with structures for clamping native tissue |
US11660187B2 (en) | 2007-09-28 | 2023-05-30 | St. Jude Medical, Llc | Collapsible-expandable prosthetic heart valves with structures for clamping native tissue |
US11534294B2 (en) | 2007-09-28 | 2022-12-27 | St. Jude Medical, Llc | Collapsible-expandable prosthetic heart valves with structures for clamping native tissue |
US11382740B2 (en) | 2007-09-28 | 2022-07-12 | St. Jude Medical, Llc | Collapsible-expandable prosthetic heart valves with structures for clamping native tissue |
US10426604B2 (en) | 2007-09-28 | 2019-10-01 | St. Jude Medical, Llc | Collapsible-expandable prosthetic heart valves with structures for clamping native tissue |
US7846199B2 (en) | 2007-11-19 | 2010-12-07 | Cook Incorporated | Remodelable prosthetic valve |
US8137394B2 (en) | 2007-12-21 | 2012-03-20 | Boston Scientific Scimed, Inc. | Valve with delayed leaflet deployment |
US8414641B2 (en) | 2007-12-21 | 2013-04-09 | Boston Scientific Scimed, Inc. | Valve with delayed leaflet deployment |
US7892276B2 (en) | 2007-12-21 | 2011-02-22 | Boston Scientific Scimed, Inc. | Valve with delayed leaflet deployment |
US11284999B2 (en) | 2008-01-24 | 2022-03-29 | Medtronic, Inc. | Stents for prosthetic heart valves |
US11259919B2 (en) | 2008-01-24 | 2022-03-01 | Medtronic, Inc. | Stents for prosthetic heart valves |
US11607311B2 (en) | 2008-01-24 | 2023-03-21 | Medtronic, Inc. | Stents for prosthetic heart valves |
US11786367B2 (en) | 2008-01-24 | 2023-10-17 | Medtronic, Inc. | Stents for prosthetic heart valves |
US11154398B2 (en) | 2008-02-26 | 2021-10-26 | JenaValve Technology. Inc. | Stent for the positioning and anchoring of a valvular prosthesis in an implantation site in the heart of a patient |
US11564794B2 (en) | 2008-02-26 | 2023-01-31 | Jenavalve Technology, Inc. | Stent for the positioning and anchoring of a valvular prosthesis in an implantation site in the heart of a patient |
US10993805B2 (en) | 2008-02-26 | 2021-05-04 | Jenavalve Technology, Inc. | Stent for the positioning and anchoring of a valvular prosthesis in an implantation site in the heart of a patient |
US20090240320A1 (en) * | 2008-03-18 | 2009-09-24 | Yosi Tuval | Valve suturing and implantation procedures |
US8313525B2 (en) | 2008-03-18 | 2012-11-20 | Medtronic Ventor Technologies, Ltd. | Valve suturing and implantation procedures |
US20100010518A1 (en) * | 2008-07-09 | 2010-01-14 | Joshua Stopek | Anastomosis Sheath And Method Of Use |
US11504228B2 (en) | 2008-07-15 | 2022-11-22 | St. Jude Medical, Llc | Collapsible and re-expandable prosthetic heart valve cuff designs and complementary technological applications |
US10010410B2 (en) | 2008-07-15 | 2018-07-03 | St. Jude Medical, Llc | Collapsible and re-expandable prosthetic heart valve cuff designs and complementary technological applications |
US9681949B2 (en) | 2008-07-15 | 2017-06-20 | St. Jude Medical, Llc | Collapsible and re-expandable prosthetic heart valve cuff designs and complementary technological applications |
US9675449B2 (en) | 2008-07-15 | 2017-06-13 | St. Jude Medical, Llc | Collapsible and re-expandable prosthetic heart valve cuff designs and complementary technological applications |
US10314694B2 (en) | 2008-07-15 | 2019-06-11 | St. Jude Medical, Llc | Collapsible and re-expandable prosthetic heart valve cuff designs and complementary technological applications |
US20110125258A1 (en) * | 2008-07-17 | 2011-05-26 | Nvt Ag | Cardiac valve prosthesis system |
CN102119013A (en) * | 2008-07-17 | 2011-07-06 | Nvt股份公司 | Cardiac valve prosthesis system |
US8747461B2 (en) | 2008-07-17 | 2014-06-10 | Nvt Ag | Cardiac valve prosthesis system |
WO2010006627A1 (en) | 2008-07-17 | 2010-01-21 | Nvt Ag | Cardiac valve prosthesis system |
US9314334B2 (en) | 2008-11-25 | 2016-04-19 | Edwards Lifesciences Corporation | Conformal expansion of prosthetic devices to anatomical shapes |
US10667906B2 (en) | 2008-11-25 | 2020-06-02 | Edwards Lifesciences Corporation | Methods of conformal expansion of prosthetic heart valves |
US11504232B2 (en) | 2008-12-19 | 2022-11-22 | Edwards Lifesciences Corporation | Rapid implant prosthetic heart valve system |
US10182909B2 (en) | 2008-12-19 | 2019-01-22 | Edwards Lifesciences Corporation | Methods for quickly implanting a prosthetic heart valve |
US9561100B2 (en) | 2008-12-19 | 2017-02-07 | Edwards Lifesciences Corporation | Systems for quickly delivering a prosthetic heart valve |
US8308798B2 (en) | 2008-12-19 | 2012-11-13 | Edwards Lifesciences Corporation | Quick-connect prosthetic heart valve and methods |
US9005278B2 (en) | 2008-12-19 | 2015-04-14 | Edwards Lifesciences Corporation | Quick-connect prosthetic heart valve |
US10799346B2 (en) | 2008-12-19 | 2020-10-13 | Edwards Lifesciences Corporation | Methods for quickly implanting a prosthetic heart valve |
US9248016B2 (en) | 2009-03-31 | 2016-02-02 | Edwards Lifesciences Corporation | Prosthetic heart valve system |
US9931207B2 (en) | 2009-03-31 | 2018-04-03 | Edwards Lifesciences Corporation | Methods of implanting a heart valve at an aortic annulus |
US9980818B2 (en) | 2009-03-31 | 2018-05-29 | Edwards Lifesciences Corporation | Prosthetic heart valve system with positioning markers |
US10842623B2 (en) | 2009-03-31 | 2020-11-24 | Edwards Lifesciences Corporation | Methods of implanting prosthetic heart valve using position markers |
US8696742B2 (en) | 2009-06-26 | 2014-04-15 | Edwards Lifesciences Corporation | Unitary quick-connect prosthetic heart valve deployment methods |
US10555810B2 (en) | 2009-06-26 | 2020-02-11 | Edwards Lifesciences Corporation | Prosthetic heart valve deployment systems |
US8348998B2 (en) | 2009-06-26 | 2013-01-08 | Edwards Lifesciences Corporation | Unitary quick connect prosthetic heart valve and deployment system and methods |
US9005277B2 (en) | 2009-06-26 | 2015-04-14 | Edwards Lifesciences Corporation | Unitary quick-connect prosthetic heart valve deployment system |
DE102009037739A1 (en) * | 2009-06-29 | 2010-12-30 | Be Innovative Gmbh | Percutaneously implantable valve stent, device for its application and method for producing the valve stent |
WO2011000354A3 (en) * | 2009-06-29 | 2011-03-03 | Be Innovative Gmbh | Percutaneously implantable flap stent, device for applying the same and method for producing the flap stent |
US9566151B2 (en) | 2009-06-29 | 2017-02-14 | Be Innovative Gmbh | Percutaneously implantable flap stent, device for applying the same and method for producing the flap stent |
US8449625B2 (en) | 2009-10-27 | 2013-05-28 | Edwards Lifesciences Corporation | Methods of measuring heart valve annuluses for valve replacement |
US10231646B2 (en) | 2009-10-27 | 2019-03-19 | Edwards Lifesciences Corporation | Device for measuring an aortic valve annulus in an expanded condition |
US9603553B2 (en) | 2009-10-27 | 2017-03-28 | Edwards Lifesciences Corporation | Methods of measuring heart valve annuluses for valve replacement |
US11412954B2 (en) | 2009-10-27 | 2022-08-16 | Edwards Lifesciences Corporation | Device for measuring an aortic valve annulus in an expanded condition |
CN107260367A (en) * | 2009-11-02 | 2017-10-20 | 西美蒂斯股份公司 | Sustainer bioprosthesis and the system for its delivering |
US10405978B2 (en) | 2010-01-22 | 2019-09-10 | 4Tech Inc. | Tricuspid valve repair using tension |
US10058323B2 (en) | 2010-01-22 | 2018-08-28 | 4 Tech Inc. | Tricuspid valve repair using tension |
US9241702B2 (en) | 2010-01-22 | 2016-01-26 | 4Tech Inc. | Method and apparatus for tricuspid valve repair using tension |
US10433963B2 (en) | 2010-01-22 | 2019-10-08 | 4Tech Inc. | Tissue anchor and delivery tool |
US10238491B2 (en) | 2010-01-22 | 2019-03-26 | 4Tech Inc. | Tricuspid valve repair using tension |
US9307980B2 (en) | 2010-01-22 | 2016-04-12 | 4Tech Inc. | Tricuspid valve repair using tension |
US8475525B2 (en) | 2010-01-22 | 2013-07-02 | 4Tech Inc. | Tricuspid valve repair using tension |
US8961596B2 (en) | 2010-01-22 | 2015-02-24 | 4Tech Inc. | Method and apparatus for tricuspid valve repair using tension |
US11833041B2 (en) | 2010-04-01 | 2023-12-05 | Medtronic, Inc. | Transcatheter valve with torsion spring fixation and related systems and methods |
US11554010B2 (en) | 2010-04-01 | 2023-01-17 | Medtronic, Inc. | Transcatheter valve with torsion spring fixation and related systems and methods |
US8652204B2 (en) | 2010-04-01 | 2014-02-18 | Medtronic, Inc. | Transcatheter valve with torsion spring fixation and related systems and methods |
US9925044B2 (en) | 2010-04-01 | 2018-03-27 | Medtronic, Inc. | Transcatheter valve with torsion spring fixation and related systems and methods |
US10716665B2 (en) | 2010-04-01 | 2020-07-21 | Medtronic, Inc. | Transcatheter valve with torsion spring fixation and related systems and methods |
US8986374B2 (en) | 2010-05-10 | 2015-03-24 | Edwards Lifesciences Corporation | Prosthetic heart valve |
US11571299B2 (en) | 2010-05-10 | 2023-02-07 | Edwards Lifesciences Corporation | Methods for manufacturing resilient prosthetic surgical heart valves |
US10702383B2 (en) | 2010-05-10 | 2020-07-07 | Edwards Lifesciences Corporation | Methods of delivering and implanting resilient prosthetic surgical heart valves |
US10463480B2 (en) | 2010-05-12 | 2019-11-05 | Edwards Lifesciences Corporation | Leaflet for low gradient prosthetic heart valve |
US11266497B2 (en) | 2010-05-12 | 2022-03-08 | Edwards Lifesciences Corporation | Low gradient prosthetic heart valves |
US9554901B2 (en) | 2010-05-12 | 2017-01-31 | Edwards Lifesciences Corporation | Low gradient prosthetic heart valve |
US9603708B2 (en) | 2010-05-19 | 2017-03-28 | Dfm, Llc | Low crossing profile delivery catheter for cardiovascular prosthetic implant |
US10478299B2 (en) | 2010-05-19 | 2019-11-19 | Dfm, Llc | Low crossing profile delivery catheter for cardiovascular prosthetic implant |
US11589981B2 (en) | 2010-05-25 | 2023-02-28 | Jenavalve Technology, Inc. | Prosthetic heart valve and transcatheter delivered endoprosthesis comprising a prosthetic heart valve and a stent |
US10722358B2 (en) | 2010-09-10 | 2020-07-28 | Edwards Lifesciences Corporation | Systems for rapidly deployable surgical heart valves |
US9370418B2 (en) | 2010-09-10 | 2016-06-21 | Edwards Lifesciences Corporation | Rapidly deployable surgical heart valves |
US10039641B2 (en) | 2010-09-10 | 2018-08-07 | Edwards Lifesciences Corporation | Methods of rapidly deployable surgical heart valves |
US8641757B2 (en) | 2010-09-10 | 2014-02-04 | Edwards Lifesciences Corporation | Systems for rapidly deploying surgical heart valves |
US9968450B2 (en) | 2010-09-10 | 2018-05-15 | Edwards Lifesciences Corporation | Methods for ensuring safe and rapid deployment of prosthetic heart valves |
US10548728B2 (en) | 2010-09-10 | 2020-02-04 | Edwards Lifesciences Corporation | Safety systems for expansion of prosthetic heart valves |
US11775613B2 (en) | 2010-09-10 | 2023-10-03 | Edwards Lifesciences Corporation | Methods of safely expanding prosthetic heart valves |
US11197757B2 (en) | 2010-09-10 | 2021-12-14 | Edwards Lifesciences Corporation | Methods of safely expanding prosthetic heart valves |
US9504563B2 (en) | 2010-09-10 | 2016-11-29 | Edwards Lifesciences Corporation | Rapidly deployable surgical heart valves |
US9125741B2 (en) | 2010-09-10 | 2015-09-08 | Edwards Lifesciences Corporation | Systems and methods for ensuring safe and rapid deployment of prosthetic heart valves |
US11471279B2 (en) | 2010-09-10 | 2022-10-18 | Edwards Lifesciences Corporation | Systems for rapidly deployable surgical heart valves |
US10736741B2 (en) | 2010-09-27 | 2020-08-11 | Edwards Lifesciences Corporation | Methods of delivery of heart valves |
US8845720B2 (en) | 2010-09-27 | 2014-09-30 | Edwards Lifesciences Corporation | Prosthetic heart valve frame with flexible commissures |
US11207178B2 (en) | 2010-09-27 | 2021-12-28 | Edwards Lifesciences Corporation | Collapsible-expandable heart valves |
US9861479B2 (en) | 2010-09-27 | 2018-01-09 | Edwards Lifesciences Corporation | Methods of delivery of flexible heart valves |
US10537423B2 (en) | 2010-10-05 | 2020-01-21 | Edwards Lifesciences Corporation | Prosthetic heart valve |
US10478292B2 (en) | 2010-10-05 | 2019-11-19 | Edwards Lifesciences Corporation | Prosthetic heart valve |
US10433958B2 (en) | 2010-10-05 | 2019-10-08 | Edwards Lifesciences Corporation | Prosthetic heart valve |
US9393110B2 (en) | 2010-10-05 | 2016-07-19 | Edwards Lifesciences Corporation | Prosthetic heart valve |
US10433959B2 (en) | 2010-10-05 | 2019-10-08 | Edwards Lifesciences Corporation | Prosthetic heart valve |
US10543080B2 (en) | 2011-05-20 | 2020-01-28 | Edwards Lifesciences Corporation | Methods of making encapsulated heart valves |
US11517426B2 (en) | 2011-05-20 | 2022-12-06 | Edwards Lifesciences Corporation | Encapsulated heart valves |
US9668859B2 (en) | 2011-08-05 | 2017-06-06 | California Institute Of Technology | Percutaneous heart valve delivery systems |
US9078747B2 (en) | 2011-12-21 | 2015-07-14 | Edwards Lifesciences Corporation | Anchoring device for replacing or repairing a heart valve |
US10238489B2 (en) | 2011-12-21 | 2019-03-26 | Edwards Lifesciences Corporation | Anchoring device and method for replacing or repairing a heart valve |
US10849752B2 (en) | 2011-12-21 | 2020-12-01 | Edwards Lifesciences Corporation | Methods for anchoring a device at a native heart valve annulus |
US11452602B2 (en) | 2011-12-21 | 2022-09-27 | Edwards Lifesciences Corporation | Anchoring device for replacing or repairing a native heart valve annulus |
US10940167B2 (en) | 2012-02-10 | 2021-03-09 | Cvdevices, Llc | Methods and uses of biological tissues for various stent and other medical applications |
US9445897B2 (en) | 2012-05-01 | 2016-09-20 | Direct Flow Medical, Inc. | Prosthetic implant delivery device with introducer catheter |
US10206673B2 (en) | 2012-05-31 | 2019-02-19 | 4Tech, Inc. | Suture-securing for cardiac valve repair |
US8961594B2 (en) | 2012-05-31 | 2015-02-24 | 4Tech Inc. | Heart valve repair system |
US9788948B2 (en) | 2013-01-09 | 2017-10-17 | 4 Tech Inc. | Soft tissue anchors and implantation techniques |
US9693865B2 (en) | 2013-01-09 | 2017-07-04 | 4 Tech Inc. | Soft tissue depth-finding tool |
US10449050B2 (en) | 2013-01-09 | 2019-10-22 | 4 Tech Inc. | Soft tissue depth-finding tool |
US11406495B2 (en) | 2013-02-11 | 2022-08-09 | Cook Medical Technologies Llc | Expandable support frame and medical device |
US9907681B2 (en) | 2013-03-14 | 2018-03-06 | 4Tech Inc. | Stent with tether interface |
US10058425B2 (en) | 2013-03-15 | 2018-08-28 | Edwards Lifesciences Corporation | Methods of assembling a valved aortic conduit |
US11007058B2 (en) | 2013-03-15 | 2021-05-18 | Edwards Lifesciences Corporation | Valved aortic conduits |
US11648116B2 (en) | 2013-03-15 | 2023-05-16 | Edwards Lifesciences Corporation | Methods of assembling valved aortic conduits |
US9744037B2 (en) | 2013-03-15 | 2017-08-29 | California Institute Of Technology | Handle mechanism and functionality for repositioning and retrieval of transcatheter heart valves |
US9968451B2 (en) | 2013-06-12 | 2018-05-15 | Edwards Lifesciences Corporation | Cardiac implant with integrated suture fasteners |
US11464633B2 (en) | 2013-06-12 | 2022-10-11 | Edwards Lifesciences Corporation | Heart valve implants with side slits |
US9468527B2 (en) | 2013-06-12 | 2016-10-18 | Edwards Lifesciences Corporation | Cardiac implant with integrated suture fasteners |
US10314706B2 (en) | 2013-06-12 | 2019-06-11 | Edwards Lifesciences Corporation | Methods of implanting a cardiac implant with integrated suture fasteners |
US10702680B2 (en) | 2013-08-28 | 2020-07-07 | Edwards Lifesciences Corporation | Method of operating an integrated balloon catheter inflation system |
US9919137B2 (en) | 2013-08-28 | 2018-03-20 | Edwards Lifesciences Corporation | Integrated balloon catheter inflation system |
US11185405B2 (en) | 2013-08-30 | 2021-11-30 | Jenavalve Technology, Inc. | Radially collapsible frame for a prosthetic valve and method for manufacturing such a frame |
US11266499B2 (en) | 2013-09-20 | 2022-03-08 | Edwards Lifesciences Corporation | Heart valves with increased effective orifice area |
US10441415B2 (en) | 2013-09-20 | 2019-10-15 | Edwards Lifesciences Corporation | Heart valves with increased effective orifice area |
US10022114B2 (en) | 2013-10-30 | 2018-07-17 | 4Tech Inc. | Percutaneous tether locking |
US10052095B2 (en) | 2013-10-30 | 2018-08-21 | 4Tech Inc. | Multiple anchoring-point tension system |
US10039643B2 (en) | 2013-10-30 | 2018-08-07 | 4Tech Inc. | Multiple anchoring-point tension system |
US10722316B2 (en) | 2013-11-06 | 2020-07-28 | Edwards Lifesciences Corporation | Bioprosthetic heart valves having adaptive seals to minimize paravalvular leakage |
US10849740B2 (en) | 2013-11-06 | 2020-12-01 | St. Jude Medical, Cardiology Division, Inc. | Paravalvular leak sealing mechanism |
US11446143B2 (en) | 2013-11-06 | 2022-09-20 | St. Jude Medical, Cardiology Division, Inc. | Paravalvular leak sealing mechanism |
US9913715B2 (en) | 2013-11-06 | 2018-03-13 | St. Jude Medical, Cardiology Division, Inc. | Paravalvular leak sealing mechanism |
US9956384B2 (en) | 2014-01-24 | 2018-05-01 | Cook Medical Technologies Llc | Articulating balloon catheter and method for using the same |
US9549816B2 (en) | 2014-04-03 | 2017-01-24 | Edwards Lifesciences Corporation | Method for manufacturing high durability heart valve |
US9585752B2 (en) | 2014-04-30 | 2017-03-07 | Edwards Lifesciences Corporation | Holder and deployment system for surgical heart valves |
US11376122B2 (en) | 2014-04-30 | 2022-07-05 | Edwards Lifesciences Corporation | Holder and deployment system for surgical heart valves |
US10307249B2 (en) | 2014-04-30 | 2019-06-04 | Edwards Lifesciences Corporation | Holder and deployment system for surgical heart valves |
US9801720B2 (en) | 2014-06-19 | 2017-10-31 | 4Tech Inc. | Cardiac tissue cinching |
US9504566B2 (en) | 2014-06-20 | 2016-11-29 | Edwards Lifesciences Corporation | Surgical heart valves identifiable post-implant |
US10130469B2 (en) | 2014-06-20 | 2018-11-20 | Edwards Lifesciences Corporation | Expandable surgical heart valve indicators |
US11154394B2 (en) | 2014-06-20 | 2021-10-26 | Edwards Lifesciences Corporation | Methods of identifying and replacing implanted heart valves |
US11717425B2 (en) | 2014-07-20 | 2023-08-08 | Restore Medical Ltd. | Pulmonary artery implant apparatus and methods of use thereof |
US10667931B2 (en) * | 2014-07-20 | 2020-06-02 | Restore Medical Ltd. | Pulmonary artery implant apparatus and methods of use thereof |
US20170172771A1 (en) * | 2014-07-20 | 2017-06-22 | Elchanan Bruckheimer | Pulmonary artery implant apparatus and methods of use thereof |
US9907547B2 (en) | 2014-12-02 | 2018-03-06 | 4Tech Inc. | Off-center tissue anchors |
US11389152B2 (en) | 2014-12-02 | 2022-07-19 | 4Tech Inc. | Off-center tissue anchors with tension members |
US11337800B2 (en) | 2015-05-01 | 2022-05-24 | Jenavalve Technology, Inc. | Device and method with reduced pacemaker rate in heart valve replacement |
USD867594S1 (en) | 2015-06-19 | 2019-11-19 | Edwards Lifesciences Corporation | Prosthetic heart valve |
USD893031S1 (en) | 2015-06-19 | 2020-08-11 | Edwards Lifesciences Corporation | Prosthetic heart valve |
US10456246B2 (en) | 2015-07-02 | 2019-10-29 | Edwards Lifesciences Corporation | Integrated hybrid heart valves |
US10695170B2 (en) | 2015-07-02 | 2020-06-30 | Edwards Lifesciences Corporation | Hybrid heart valves adapted for post-implant expansion |
US11654020B2 (en) | 2015-07-02 | 2023-05-23 | Edwards Lifesciences Corporation | Hybrid heart valves |
US11690714B2 (en) | 2015-07-02 | 2023-07-04 | Edwards Lifesciences Corporation | Hybrid heart valves adapted for post-implant expansion |
US11690709B2 (en) | 2015-09-02 | 2023-07-04 | Edwards Lifesciences Corporation | Methods for securing a transcatheter valve to a bioprosthetic cardiac structure |
US10080653B2 (en) | 2015-09-10 | 2018-09-25 | Edwards Lifesciences Corporation | Limited expansion heart valve |
US11806232B2 (en) | 2015-09-10 | 2023-11-07 | Edwards Lifesciences Corporation | Limited expansion valve-in-valve procedures |
US10751174B2 (en) | 2015-09-10 | 2020-08-25 | Edwards Lifesciences Corporation | Limited expansion heart valve |
US20170156863A1 (en) * | 2015-12-03 | 2017-06-08 | Medtronic Vascular, Inc. | Venous valve prostheses |
US10973640B2 (en) | 2015-12-03 | 2021-04-13 | Medtronic Vascular, Inc. | Venous valve prostheses |
US11684476B2 (en) | 2015-12-03 | 2023-06-27 | Medtronic Vascular, Inc. | Venous valve prostheses |
US10143554B2 (en) * | 2015-12-03 | 2018-12-04 | Medtronic Vascular, Inc. | Venous valve prostheses |
CN105496607A (en) * | 2016-01-11 | 2016-04-20 | 北京迈迪顶峰医疗科技有限公司 | Aortic valve device conveyed by catheter |
US10667904B2 (en) | 2016-03-08 | 2020-06-02 | Edwards Lifesciences Corporation | Valve implant with integrated sensor and transmitter |
US11471275B2 (en) | 2016-03-08 | 2022-10-18 | Edwards Lifesciences Corporation | Valve implant with integrated sensor and transmitter |
US11065138B2 (en) | 2016-05-13 | 2021-07-20 | Jenavalve Technology, Inc. | Heart valve prosthesis delivery system and method for delivery of heart valve prosthesis with introducer sheath and loading system |
US10456245B2 (en) | 2016-05-16 | 2019-10-29 | Edwards Lifesciences Corporation | System and method for applying material to a stent |
US11890017B2 (en) | 2016-09-28 | 2024-02-06 | Restore Medical Ltd. | Artery medical apparatus and methods of use thereof |
US11771434B2 (en) | 2016-09-28 | 2023-10-03 | Restore Medical Ltd. | Artery medical apparatus and methods of use thereof |
EP3528748B2 (en) † | 2016-10-24 | 2024-02-14 | Nvt Ag | Intraluminal vessel prosthesis for implantation into the heart or cardiac vessels of a patient |
EP3528748B1 (en) | 2016-10-24 | 2021-01-20 | Nvt Ag | Intraluminal vessel prosthesis for implantation into the heart or cardiac vessels of a patient |
US11007055B2 (en) * | 2016-10-24 | 2021-05-18 | Nvt Ag | Intraluminal vascular prosthesis for implantation into the heart or cardiovascular vessels of a patient |
USD846122S1 (en) | 2016-12-16 | 2019-04-16 | Edwards Lifesciences Corporation | Heart valve sizer |
US11197754B2 (en) | 2017-01-27 | 2021-12-14 | Jenavalve Technology, Inc. | Heart valve mimicry |
US11376125B2 (en) | 2017-04-06 | 2022-07-05 | Edwards Lifesciences Corporation | Prosthetic valve holders with automatic deploying mechanisms |
US10463485B2 (en) | 2017-04-06 | 2019-11-05 | Edwards Lifesciences Corporation | Prosthetic valve holders with automatic deploying mechanisms |
US10799353B2 (en) | 2017-04-28 | 2020-10-13 | Edwards Lifesciences Corporation | Prosthetic heart valve with collapsible holder |
US11911273B2 (en) | 2017-04-28 | 2024-02-27 | Edwards Lifesciences Corporation | Prosthetic heart valve with collapsible holder |
US11364132B2 (en) | 2017-06-05 | 2022-06-21 | Restore Medical Ltd. | Double walled fixed length stent like apparatus and methods of use thereof |
US11135057B2 (en) | 2017-06-21 | 2021-10-05 | Edwards Lifesciences Corporation | Dual-wireform limited expansion heart valves |
US10806579B2 (en) | 2017-10-20 | 2020-10-20 | Boston Scientific Scimed, Inc. | Heart valve repair implant for treating tricuspid regurgitation |
US11337805B2 (en) | 2018-01-23 | 2022-05-24 | Edwards Lifesciences Corporation | Prosthetic valve holders, systems, and methods |
US20190351099A1 (en) * | 2018-05-21 | 2019-11-21 | Aran Biomedical Teoranta | Insertable medical devices with low profile composite coverings |
USD995774S1 (en) | 2018-07-11 | 2023-08-15 | Edwards Lifesciences Corporation | Collapsible heart valve sizer |
USD952143S1 (en) | 2018-07-11 | 2022-05-17 | Edwards Lifesciences Corporation | Collapsible heart valve sizer |
USD908874S1 (en) | 2018-07-11 | 2021-01-26 | Edwards Lifesciences Corporation | Collapsible heart valve sizer |
US11554012B2 (en) | 2019-12-16 | 2023-01-17 | Edwards Lifesciences Corporation | Valve holder assembly with suture looping protection |
US11951006B2 (en) | 2019-12-16 | 2024-04-09 | Edwards Lifesciences Corporation | Valve holder assembly with suture looping protection |
US11857417B2 (en) | 2020-08-16 | 2024-01-02 | Trilio Medical Ltd. | Leaflet support |
Also Published As
Publication number | Publication date |
---|---|
WO2003094799A1 (en) | 2003-11-20 |
CA2501712C (en) | 2010-07-20 |
DE60332938D1 (en) | 2010-07-22 |
MXPA04011147A (en) | 2005-07-01 |
WO2004034933A2 (en) | 2004-04-29 |
EP1509171B1 (en) | 2010-06-09 |
AU2009200209B2 (en) | 2011-02-03 |
CA2485293A1 (en) | 2003-11-20 |
JP2005525172A (en) | 2005-08-25 |
EP2149350A3 (en) | 2010-04-28 |
AU2003230363A1 (en) | 2003-11-11 |
EP1667604A2 (en) | 2006-06-14 |
EP1507492A1 (en) | 2005-02-23 |
US20040019374A1 (en) | 2004-01-29 |
AU2003225291A1 (en) | 2003-11-11 |
US20030225447A1 (en) | 2003-12-04 |
EP1667604B1 (en) | 2014-08-20 |
MXPA04011144A (en) | 2005-08-16 |
AU2003298515A1 (en) | 2004-05-04 |
WO2003094795A1 (en) | 2003-11-20 |
JP2005525169A (en) | 2005-08-25 |
CA2501712A1 (en) | 2004-04-29 |
EP1509171A1 (en) | 2005-03-02 |
CA2485285A1 (en) | 2003-11-20 |
ATE470406T1 (en) | 2010-06-15 |
EP2149350A2 (en) | 2010-02-03 |
WO2004034933A9 (en) | 2004-06-03 |
US7758632B2 (en) | 2010-07-20 |
MXPA04011148A (en) | 2005-08-16 |
AU2009200209A1 (en) | 2009-03-12 |
AU2009200210A1 (en) | 2009-02-19 |
WO2004034933A3 (en) | 2004-07-08 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
EP1509171B1 (en) | Unidirectional flow prosthetic implant based on a multi-lobed frame | |
US7485141B2 (en) | Method of placing a tubular membrane on a structural frame | |
US7351256B2 (en) | Frame based unidirectional flow prosthetic implant | |
US8663541B2 (en) | Method of forming a tubular membrane on a structural frame |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
AS | Assignment |
Owner name: CORDIS CORPORATION, FLORIDA Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:HOJEIBANE, HIKMAT;MAJERCAK, DAVID CHRISTOPHER;REEL/FRAME:013925/0108 Effective date: 20030716 |
|
STCB | Information on status: application discontinuation |
Free format text: ABANDONED -- FAILURE TO RESPOND TO AN OFFICE ACTION |