US20050143807A1 - Implantable vascular device comprising a bioabsorbable frame - Google Patents
Implantable vascular device comprising a bioabsorbable frame Download PDFInfo
- Publication number
- US20050143807A1 US20050143807A1 US10/910,490 US91049004A US2005143807A1 US 20050143807 A1 US20050143807 A1 US 20050143807A1 US 91049004 A US91049004 A US 91049004A US 2005143807 A1 US2005143807 A1 US 2005143807A1
- Authority
- US
- United States
- Prior art keywords
- valve
- frame
- implantation
- leaflet
- edge
- 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
- A61F2/2475—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
- A61F2/01—Filters implantable into blood vessels
-
- 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
- A61F2/01—Filters implantable into blood vessels
- A61F2002/018—Filters implantable into blood vessels made from tubes or sheets of material, e.g. by etching or laser-cutting
-
- 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
- A61F2220/0008—Fixation appliances for connecting prostheses to the body
-
- 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
- A61F2220/0008—Fixation appliances for connecting prostheses to the body
- A61F2220/0016—Fixation appliances for connecting prostheses to the body with sharp anchoring protrusions, e.g. barbs, pins, spikes
-
- 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
- A61F2220/0075—Connections or couplings between prosthetic parts, e.g. between modular parts; Connecting elements sutured, ligatured or stitched, retained or tied with a rope, string, thread, wire or cable
-
- 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
- A61F2230/0004—Rounded shapes, e.g. with rounded corners
- A61F2230/0008—Rounded shapes, e.g. with rounded corners elliptical or oval
-
- 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
- A61F2230/0004—Rounded shapes, e.g. with rounded corners
- A61F2230/001—Figure-8-shaped, e.g. hourglass-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
- A61F2230/0002—Two-dimensional shapes, e.g. cross-sections
- A61F2230/0017—Angular shapes
- A61F2230/0023—Angular shapes triangular
-
- 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
- A61F2230/0017—Angular shapes
- A61F2230/0026—Angular shapes trapezoidal
-
- 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
- A61F2230/0002—Two-dimensional shapes, e.g. cross-sections
- A61F2230/0028—Shapes in the form of latin or greek characters
- A61F2230/0058—X-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
- A61F2230/0095—Saddle-shaped
-
- Y—GENERAL TAGGING OF NEW TECHNOLOGICAL DEVELOPMENTS; GENERAL TAGGING OF CROSS-SECTIONAL TECHNOLOGIES SPANNING OVER SEVERAL SECTIONS OF THE IPC; TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y10—TECHNICAL SUBJECTS COVERED BY FORMER USPC
- Y10S—TECHNICAL SUBJECTS COVERED BY FORMER USPC CROSS-REFERENCE ART COLLECTIONS [XRACs] AND DIGESTS
- Y10S623/00—Prosthesis, i.e. artificial body members, parts thereof, or aids and accessories therefor
- Y10S623/901—Method of manufacturing prosthetic device
Definitions
- This invention relates to medical devices, more particularly, to intraluminal devices.
- stents and related devices Some of the chief goals in designing stents and related devices include providing sufficient radial strength to supply sufficient force to the vessel and prevent device migration.
- Self-expanding stents are superior in this regard to balloon expandable stents which are more popular for coronary use.
- the challenge is designing a device that can be delivered intraluminally to the target, while still being capable of adequate expansion.
- Self-expanding stents usually require larger struts than balloon expandable stents, thus increasing their profile. When used with fabric or other coverings that require being folded for placement into a delivery catheter, the problem is compounded.
- a basic stent including a fabric or biomaterial covering, that is capable of being delivered with a low profile, while still having a sufficient expansion ratio to permit implantation in larger vessels, if desired, while being stable, self-centering, and capable of conforming to the shape of the vessel.
- a intraluminal valve that can be deployed in vessels to replace or augment incompetent native valves, such as in the lower extremity venous system to treat patients with venous valve insufficiency.
- Such a valve should closely simulate the normal functioning valve and be capable of permanent implantation with excellent biocompatibility.
- the foregoing problems are solved and a technical advance is achieved in an illustrative implantable valve that is deployed within a bodily passage, such as a blood vessel or the heart, to regulate or augment the normal flow of blood or other bodily fluids.
- the valve includes a covering having oppositely facing curvilinear-shaped surfaces (upper and lower) against which fluid traveling in a first or second direction within the bodily passage exerts force to at least partially open or close the valve. At least one outer edge of the covering resiliently engages and exerts force against the wall of the vessel and has arcuate shape that provides at least a partial seal against the wall.
- the covering comprises a plurality of leaflets, each leaflet having a body extending from a wall-engaging outer edge to a free edge which is cooperable with one or more opposing leaflets to prevent flow in one direction, such as retrograde flow, while at least a portion of the leaflets having sufficient flexibility, when in situ to move apart, thereby creating a valve orifice that permits flow in the opposite direction, such as normal blood flow.
- the outer edge of each leaflet is adapted to engage and resilient exert force against a wall of the bodily passage such that it extends in both a longitudinal and circumferential directions along the vessel wall to at least partially seal a portion of the vessel lumen, while the free edge of each leaflet traverses the passageway across the diameter of the vessel.
- the valve in another aspect of the invention, includes a frame that is covered by a piece of biocompatible material, preferably an Extracellular Collagen Matrix (ECM) such as small intestinal submucosa (SIS) or another type of submucosal-derived tissue.
- ECM Extracellular Collagen Matrix
- SIS small intestinal submucosa
- Other potential biomaterials include allographs such as harvested native valve tissue. The material is slit or otherwise provided with an opening along one axis to form two triangular valve leaflets over a four-sided frame. In the deployed configuration, the leaflets are forced open by normal blood flow and subsequently close together in the presence of backflow to help eliminate reflux.
- Other configurations include a two-leaflet valve having an oval or elliptically shaped frame, and valves having three or more legs and associated leaflets, which provide a better distribution of the load exerted by the column of fluid acting on the leaflets.
- the frame of the device is modified by placing one or more of the bends under tension which results in the frame assuming a second shape that has superior characteristics of placement within the vessel.
- One method of adjusting the shape includes forming the bends in the wire at an initial angle, e.g., 150 ⁇ , that is larger than the desired final angle, e.g., 90 ⁇ for a four-sided valve, so when the frame is constrained into the final configuration, the sides are arcuate and bow outward slightly. The curvature of the sides allows the sides to better conform to the rounded countours of the vessel wall when the valve is deployed.
- a second method of modifying the shape is to use the material to constrain the frame in one axis.
- One such embodiment includes a four-sided valve with two triangular-shaped halves of material, such as SIS, where the material constrains the frame in a diamond shape. This puts the bend of the frame under stress or tension which permits better positioning within the vessel. It also allows the diagonal axis of the frame with the slit or orifice to be adjusted to the optimal length to properly size the frame for the vessel such that the leaflets open to allow sufficient flow, but do not open to such a degree that they contact the vessel wall.
- the potential benefits of both adding tension to the bends to bow the sides and constraining the frame into a diamond shape using the covering can be combined in a single embodiment or employed separately.
- the device in still another aspect of the present invention, includes a frame that in one embodiment, is formed from a single piece of wire or other material having a plurality of sides and bends each interconnecting adjacent sides.
- the bends can be coils, fillets, or other configurations to reduce stress and improve fatigue properties.
- the single piece of wire is preferably joined by an attachment mechanism, such as a piece of cannula and solder, to form a closed circumference frame.
- the device has a first configuration wherein the sides and bends generally lie within a single, flat plane.
- the frame is folded into a second configuration where opposite bends are brought in closer proximity to one another toward one end of the device, while the other opposite ends are folded in closer proximity together toward the opposite end of the device.
- the device becomes a self-expanding stent.
- the device is compressed into a delivery device, such as a catheter, such that the sides are generally beside one another. While the preferred embodiment is four-sided, other polygonal shapes can be used as well.
- the frame can either be formed into a generally flat configuration, or into the serpentine configuration for deployment. Besides rounded wire, the frame can comprise wires of other cross-sectional shapes (e.g., oval, delta, D-shape), or flat wire. Additionally, the frame can be molded from a polymer or composite material, or formed from a bioabsorbable material such as polyglycolic acid and materials with similar properties.
- Another method is to laser cut the frame out of a metal tube, such as stainless steel or nitinol. Still yet another method is to spot weld together, or otherwise attach, a series of separate struts that become the sides of a closed frame.
- the frame can be left with one or more open gaps that are bridged by the material stretched over the remainder of the frame.
- the frame can also be formed integrally with the covering, typically as a thickened or strengthened edge portion that gives the device sufficient rigidity to allow it to assume the deployed configuration in the vessel.
- the device can be formed into the serpentine configuration and a circumferentially constraining mechanism, such as a tether, strut, sleeve, etc., placed around the device, or built into the frame, to expand or unfold during deployment of the device to limit its expansion to a given diameter, such as that which is slightly larger than the vessel into which it is placed to allow anchoring, but not permit the device to exert to great a force on the vessel wall.
- a circumferentially constraining mechanism such as a tether, strut, sleeve, etc.
- one or more barbs can be attached to the frame for anchoring the device in the lumen of a vessel.
- the barbs can be extensions of the single piece of wire or other material comprising the frame, or they can represent a second piece of material that is separately attached to the frame by a separate attachment mechanism.
- An elongated barb can be used to connect additional devices with the second and subsequent frames attached to the barb in a similar manner. Additional barbs can be secured to the device from cannulae placed over the frame.
- the frame is formed as a single piece, such as when cut from a sheet of material or injection molded, the barbs can be formed as integral extensions of the frame.
- a covering which can be a flexible synthetic material such as DACRON, or expanded polytetrafluorethylene (ePTFE), or a natural or collagen-based material, such as an allographic tissue (such as valvular material) or a xenographic implant (such as SIS), can be attached to the device with sutures or other means to partially, completely, or selectively restrict fluid flow.
- a covering When the covering extends over the entire aperture of the frame, the frame formed into the second configuration functions as an vascular occlusion device that once deployed, is capable of almost immediately occluding an artery.
- An artificial valve such as that used in the lower legs and feet to correct incompetent veins, can be made by covering half of the frame aperture with a triangular piece of material.
- the artificial valve traps retrograde blood flow and seals the lumen, while normal blood flow is permitted to travel through the device.
- the device can be used to form a stent graft for repairing damaged or diseased vessels.
- a pair of covered frames or stent adaptors are used to secure a tubular graft prosthesis at either end and seal the vessel.
- Each stent adaptor has an opening through which the graft prosthesis is placed and an elongated barb is attached to both frames.
- one or more frames in the second configuration are used inside a sleeve to secure the device to a vessel wall.
- FIG. 1 depicts a top view of one exemplary embodiment of the present invention
- FIG. 2 depicts a pictorial view of the embodiment of FIG. 1 ;
- FIGS. 3, 3A and 3 B depict a top view and enlarged, partial cross-sectional views of a second exemplary embodiment of the present invention
- FIG. 4 depicts a side view of the embodiment of FIG. 3 deployed in a vessel
- FIG. 5 depicts a enlarged partial view of the embodiment of FIG. 1 ;
- FIG. 6 depicts a partially-sectioned side view of the embodiment of FIG. 1 inside a delivery system
- FIG. 7 depicts a top view of a third embodiment of the present invention.
- FIG. 8 depicts a side view of the embodiment of FIG. 7 deployed in a vessel
- FIGS. 9, 10 and 11 depict enlarged partial views of other embodiments of the present invention.
- FIG. 12 depicts a top view of a fourth embodiment of the present invention.
- FIGS. 13 and 14 depicts side views of the embodiment of FIG. 12 ;
- FIG. 15 depicts a top view of a fifth embodiment of the present invention.
- FIG. 16 depicts a side view of the embodiment of FIG. 15 ;
- FIG. 17 depicts a side view of a sixth embodiment of the present invention.
- FIG. 18 depicts an enlarged pictorial view of a seventh embodiment of the present invention.
- FIG. 19 depicts a top view of an eighth embodiment of the present invention.
- FIG. 20 depicts a top view of a first embodiment of a multi-leaflet intraluminal valve of the present invention
- FIG. 21 depicts a top view of a second embodiment of a multi-leaflet intraluminal valve
- FIG. 21A depicts a partial top view of another embodiment of leaflets of the present invention.
- FIG. 21B depicts a top view of another embodiment of leaflet of the present invention.
- FIGS. 22 and 23 depict side views of the embodiment of FIG. 21 when deployed in a vessel
- FIGS. 24 and 25 depict pictorial views of the embodiments of FIG. 21 when deployed in a vessel;
- FIGS. 26 and 26 A depict the method of attaching the covering to the embodiment of FIG. 21 ;
- FIG. 27 depicts a pictorial view of the basic valve of FIG. 21 upon deployment with an alternative leaflet embodiment
- FIGS. 28, 29 , 30 and 31 depict top views of selected embodiments of the present invention, made using the method shown in FIG. 28 ;
- FIG. 32 depicts a pictorial view of an embodiment of a stent graft that includes stent adaptors of the present invention
- FIG. 33 depicts a delivery system for deploying an embodiment of the present invention.
- FIG. 34 depicts a pictorial view of the present invention having returned to the first configuration following formation into the second configuration
- FIGS. 35 and 36 depict top views of a three-leg valve embodiment of the present invention, before and after being constrained;
- FIG. 37 depicts a pictorial view of the embodiment of FIG. 35 in the deployed configuration
- FIGS. 38 and 39 depict top views of four-leg valve embodiments of the present invention, before and after being constrained;
- FIG. 40 depicts a pictorial view of the embodiment of FIG. 38 in the deployed configuration
- FIG. 41 depicts a top view of a frame formed from a sheet of material
- FIG. 41A depicts a detail view of the embodiment of FIG. 41 ;
- FIG. 42 depicts a top view of a third embodiment of an intraluminal valve
- FIG. 43 depicts a pictorial view a frame embodiment formed into a deployed configuration
- FIG. 44 depicts a top view of an embodiment of implantable valve having an integrally formed frame and covering
- FIG. 45 depicts a cross-sectional view taken along line 45 - 45 of FIG. 44 ;
- FIG. 46 depicts a cross-sectional view of a second embodiment of valve having an integrally formed frame and covering
- FIG. 47 depicts a top view of an intraluminal valve embodiment having an open frame
- FIGS. 48 and 49 depict a pictorial views of an intraluminal valve embodiments that includes a circumferentially constraining mechanism
- FIG. 50 depicts a top view of the embodiment of FIG. 22 .
- FIGS. 1 - 11 , 18 - 19 are directed to a basic stent frame;
- FIGS. 12-14 are directed to a single-leaflet valve;
- FIGS. 15-16 are directed to an occluder (or filter);
- FIGS. 17 and 32 are directed to a stent adaptor for a stent graft,
- FIG. 20-27 , 35 - 40 , 42 - 50 are directed to a multi-leaf valve;
- FIG. 28-31 are directed to a constrained frame which can be used to form any of the other embodiments.
- FIG. 1 depicts a top view of one embodiment of the medical device 10 of the present invention comprising a frame 11 of resilient material, preferably metal wire made of stainless steel or a superelastic alloy (e.g., nitinol). While round wire is depicted in each of the embodiments shown herein, other types, e.g., flat, square, triangular, D-shaped, delta-shaped, etc. may be used to form the frame.
- the frame comprises a closed circumference 62 of a single piece 59 of material that is formed into a device 10 having a plurality of sides 13 interconnected by a series of bends 12 .
- the depicted embodiment includes four sides 13 of approximately equal length.
- FIG. 19 includes a four-sided frame 11 having the general shape of a kite with two adjacent longer sides 66 and two adjacent shorter sides 67 .
- the bends 12 interconnecting the sides 13 comprise a coil 14 of approximately one and a quarter turns. The coil bend produces superior bending fatigue characteristics than that of a simple bend 40 , as shown in FIG. 9 , when the frame is formed from stainless steel and most other standard materials.
- FIG. 9 The embodiment of FIG.
- the bend 12 should be of a structure that minimizes bending fatigue.
- Alternative bend 12 embodiments include an outward-projecting fillet 41 as shown in FIG. 10 , and an inward-projecting fillet 42 comprising a series of curves 63 , as shown in FIG. 11 . Fillets are well known in the stent art as a means to reduce stresses in bends. By having the fillet extend inward as depicted in FIG. 11 , there is less potential trauma to the vessel wall.
- the size of the wire which should be selected depends on the size of device and the application.
- An occlusion device for example, preferably uses 0.010′′ wire for a 10 mm square frame, while 0.014′′ and 0.016′′ wire would be used for 20 mm and 30 mm frames, respectively. Wire that is too stiff can damage the vessel, not conform well to the vessel wall, and increase the profile of the device when loaded in the delivery system prior to deployment.
- the single piece 59 of material comprising the frame 11 is formed into the closed circumference 62 by securing the first and second ends 60 , 61 with an attachment mechanism 15 such as a piece of metal cannula.
- the ends 60 , 61 of the single piece 59 are then inserted into the cannula 15 and secured with solder 25 , a weld, adhesive, or crimping to form the closed frame 11 .
- the ends 60 , 61 of the single piece 59 can be joined directly without addition of a cannula 15 , such as by soldering, welding, or other methods to join ends 61 and 62 .
- the frame could be fabricated as a single piece of material 59 , by stamping or cutting the frame 11 from another sheet (e.g., with a laser), fabricating from a mold, or some similar method of producing a unitary frame.
- the device 10 depicted in FIG. 1 is shown in its first configuration 35 whereby all four bends 20 , 21 , 22 , 23 and each of the sides 13 generally lie within a single flat plane.
- a second configuration 36 shown in FIG. 2
- the frame 11 of FIG. 1 is folded twice, first along one diagonal axis 94 with opposite bends 20 and 21 being brought into closer proximity, followed by opposite bends 22 and 23 being folded together and brought into closer proximity in the opposite direction.
- the second configuration 36 depicted in FIG.
- the medical device in the second configuration 36 can be used as a stent 44 to maintain an open lumen 34 in a vessel 33 , such as a vein, artery, or duct.
- the bending stresses introduced to the frame 11 by the first and second folds required to form the device 10 into the second configuration 36 apply force radially outward against the vessel wall 70 to hold the device 10 in place and prevent vessel closure.
- the device in the second configuration 36 when not with the vessel or other constraining means will at least partially return to the first configuration 25 , although some deformation can occur as depicted in FIG. 34 , depending on the material used. It is possible to plastically form the stent into this configuration which represents an intermediate condition between the first configuration (which it also can obtain) and the second configuration. It is also possible to plastically deform the device 10 into the second configuration 36 , such that it does not unfold when restraint is removed. This might be particularly desired if the device is made from nitinol or a superelastic alloy.
- the standard method of deploying the medical device 10 in a vessel 33 involves resiliently forming the frame 11 into a third configuration 37 to load into a delivery device 26 , such as a catheter.
- a delivery device 26 such as a catheter.
- the adjacent sides 13 are generally beside each other in close proximity extending generally along the same axis.
- a pusher 27 is placed into the catheter lumen 29 .
- the device 10 When the device 10 is fully deployed, it assumes the second configuration 36 within the vessel as depicted in FIG. 2 .
- the sides 13 of the frame being made of resilient material, conform to the shape of the vessel wall 70 such that when viewed on end, the device 10 has a circular appearance when deployed in a round vessel. As a result, sides 13 are arcuate or slightly bowed out to better conform to the vessel wall.
- a second embodiment of the present invention is depicted in FIG. 3 wherein one or more barbs 16 are included to anchor the device 10 following deployment.
- a barb can be a wire, hook, or any structure attached to the frame and so configured as to be able to anchor the device 10 within a lumen.
- the illustrative embodiment includes a first barb 16 with up to three other barbs 17 , 71 , 72 , indicated in dashed lines, representing alternative embodiments.
- the barb combination 38 that comprises barbs 17 and 18 , each barb is an extension of the single piece 59 of material of the frame 11 beyond the closed circumference 59 .
- the attachment cannula 15 secures and closes the single piece 59 of material into the frame 11 as previously described, while the first and second ends 60 , 61 thereof, extend from the cannula 15 , running generally parallel with the side 13 of the frame 11 from which they extend, each preferably terminating around or slightly beyond respective bends 20 , 23 .
- the distal end 19 of the barb 16 in the illustrative embodiment contains a bend or hook.
- the tip of the distal end 19 can be ground to a sharpened point for better tissue penetration.
- a double ended barb 39 comprising barbs 71 and 72 is attached to the opposite side 13 as defined by bends 21 and 22 .
- the double barb 39 as shown in detail view B of FIG. 3 , comprises a piece of wire, usually the length of barb combination 38 , that is separate from the single piece 59 comprising the main frame 11 . It is secured to the frame by attachment mechanism 15 using the methods described for FIG. 1 .
- FIG. 4 depicts barb 17 (and 18 ) engaging the vessel wall 70 while the device 10 is in the second, deployed configuration 36 . While this embodiment describes up to a four barb system, more than four can be used.
- FIG. 7 depicts a top view of a third embodiment of the present invention in the first configuration 35 that includes a plurality of frames 11 attached in series.
- a first frame 30 and second frame 31 are attached by a barb 16 that is secured to each frame by their respective attachment mechanisms 15 .
- the barb 16 can be a double-ended barb 39 as shown in FIG. 3 (and detail view B) that is separate from the single pieces 59 comprising frames 30 and 31 , or the barb may represent a long extended end of the one of the single pieces 59 as shown in detail view A of FIG. 3 .
- Further frames, such as third frame 32 shown in dashed lines, can be added by merely extending the length of the barb 16 .
- FIG. 8 depicts a side view of the embodiment of FIG. 7 in the second configuration 36 as deployed in a vessel 33 .
- FIGS. 12-18 depict embodiments of the present invention in which a covering 45 comprising a sheet of fabric, collagen (such as small intestinal submucosa), or other flexible material is attached to the frame 11 by means of sutures 50 , adhesive, heat sealing, A weaving@ together, crosslinking, or other known means.
- FIG. 12 depicts a top view of a fourth embodiment of the present invention while in the first configuration 35 , in which the covering 45 is a partial covering 58 , triangular in shape, that extends over approximately half of the aperture 56 of the frame 11 .
- the device 10 can act as an artificial valve 43 such as the type used to correct valvular incompetence.
- FIG. 13 depicts the valve 43 in the open configuration 48 .
- the partial covering 58 has been displaced toward the vessel wall 70 due to positive fluid pressure or flow in a first direction 46 , e.g., normal venous blood flow, thereby opening a passageway 65 through the frame 11 and the lumen 34 of the vessel 33 .
- a first direction 46 e.g., normal venous blood flow
- the partial covering 58 acts as a normal valve by catching the backward flowing blood and closing the lumen 34 of the vessel.
- the partial covering 58 is forced against the vessel wall to seal off the passageway 65 , unlike a normal venous valve which has two leaflets, which are forced together during retrograde flow.
- Both the artificial valve 43 of the illustrative embodiment and the normal venous valve have a curved structure or cusp that facilitates the capture of the blood and subsequent closure.
- other possible configurations of the partial covering 58 that result in the cupping or trapping of fluid in one direction can be used.
- FIG. 15 depicts a top view of a fifth embodiment of the present invention in the first configuration 35 , whereby there is a full covering 57 that generally covers the entire aperture 56 of the frame 11 .
- the device 10 When the device 10 is formed into the second configuration 36 , as depicted in FIG. 16 , it becomes useful as an occlusion device 51 to occlude a duct or vessel, close a shunt, repair a defect, or other application where complete or substantially complete prevention of flow is desired.
- studies in swine have shown occlusion to occur almost immediately when deployed in an artery or the aorta with autopsy specimens showing that thrombus and fibrin which had filled the space around the device.
- the design of the present invention permits it to be used successfully in large vessels such as the aorta.
- the occlusion device should have side 13 lengths that are at least around 50% or larger than the vessel diameter in which they are to be implanted.
- FIGS. 17-18 depict two embodiments of the present invention in which the device 10 functions as a stent graft 75 to repair a damaged or diseased vessel, such as due to formation of an aneurysm.
- FIG. 17 shows a stent graft 75 having a tubular graft prosthesis 54 that is held in place by a pair of frames 11 that function as stent adaptors 52 , 53 .
- Each stent adaptor 52 , 53 has a covering attached to each of the frame sides 13 which includes a central opening 55 through which the graft prosthesis 54 is placed and held in place by friction or attachment to prevent migration.
- One method of preventing migration is placement of a stent adaptor 52 , 53 according to the present invention at each end and suturing the graft prosthesis 54 to the covering of the stent adaptors 52 , 53 .
- the stent adaptors 52 , 53 provide a means to seal blood flow while centering the graft prosthesis in the vessel.
- a long double-ended barb 39 connects to each stent adaptor 52 , 53 and assists to further anchor the stent graft 75 .
- the covering 45 comprises a outer sleeve 64 that is held in place by first and second 30 , 31 frames that function as stents 44 to hold and seal the sleeve 64 against a vessel wall and maintain an open passageway 65 .
- the stents 44 are secured to the graft sleeve 64 by sutures 50 that are optionally anchored to the coils 14 of the bends 12 . If the embodiment of FIG. 18 is used in smaller vessels, a single frame 11 can be used at each end of the stent graft 75 . Another stent graft 75 embodiment is depicted in FIG.
- the stent adaptor 52 of the present invention is placed in the common vessel 96 such as the abdominal aorta.
- Two tubular grafts 54 are secured within an aperture 55 in the covering 45 of the frame 11 by one or more internal stent adapters 102 , or another type of self-expanding stent, that bias the opening of the grafts 54 against the surrounding covering 45 to provide an adequate seal.
- Each leg 98 , 99 of the stent graft prosthesis 75 transverses the vessel defect 97 and feeds into their respective vessel branches 100 , 101 such the right and left common iliac arteries.
- a second stent adapter 53 can be used to anchor the other end of the tubular graft 54 in each vessel branch 100 , 101 .
- FIGS. 20-27 and 35 - 41 depict embodiments of present inventions in which the device 10 comprises an implantable valve having multiple leaflets 25 that act together to regulate and augment the flow of fluid through a duct or vessel 33 , or within the heart to treat patients with damaged or diseased heart valves.
- the covering 45 of each of these embodiments includes one or a series of partial coverings 58 that form the leaflets 25 of the valve. As with the other embodiments, the covering 45 may comprise a biomaterial or a synthetic material.
- DACRON, expanded polytetrafluoroethylene (ePTFE), or other synthetic biocompatible materials can be used to fabricate the covering 45
- a naturally occurring biomaterial such as collagen
- ECM extracellular matrix
- SIS is particularly useful, and can be made in the fashion described in Badylak et al., U.S. Pat. No. 4,902,508; Intestinal Collagen Layer described in U.S. Pat. No.
- autologous tissue can be harvested as well, for use in forming the leaflets of the valve.
- Elastin or Elastin Like Polypetides (ELPs) and the like offer potential as a material to fabricate the covering or frame to form a device with exceptional biocompatibility.
- Another alternative would be to used allographs such as harvested native valve tissue. Such tissue is commercially available in a cryopreserved state.
- valve 43 is divided into a plurality of legs 113 , each of which further comprises a leaflet 25 .
- a separate or integral frame 11 is included, such as the wire frame 11 depicted in FIG. 1 .
- the wire used to construct the frame is made of a resilient material such as 302 , 304 stainless steel; however, a wide variety of other metals, polymers, or other materials are possible. It is possible for the frame to be made of the same material as the leaflets 25 .
- a suitable frame material would be a superelastic alloy such as nitinol (NiTi).
- Resiliency of the frame 11 which provides radial expandability to the valve 43 when in the second configuration 36 for deployment, is not necessarily an essential property of the frame.
- optional barbs 16 can provide the means to anchor the valve 43 after delivery, even if the valve 43 lacks sufficient expansile force to anchor itself against the vessel wall.
- the frame can comprise a ductile material with the device 10 being designed to be balloon expandable within the vessel.
- the valve 43 in situ comprises a plurality of bends 12 of the frame, that provide the majority of the outward radial force that helps anchor the device to vessel wall 70 , as depicted in FIGS. 22-27 .
- the frame assumes the undulating or serpentine configuration characteristic of the invention with a first series of bends 115 of the first or proximal end alternating with a second series of bends 116 of the second or distal end, with the second or distal bends 116 being located at the bottom of the valve distal to the heart and the first or proximal bends 115 being located at the top of the valve proximal to the heart.
- the central portion or body 156 of the leaflet 25 extends inward from the vessel wall 70 and outer edge 112 in an oblique direction toward the first end 68 of the valve 43 where it terminates at the inner edge 111 thereof.
- the valve leaflets that come in contact with the vessel wall can also be arcuate as the supporting frame to better conform to and seal wit the vessel wall.
- the leaflets 25 assume a curvilinear shape when in the deployed configuration 36 .
- FIGS. 20-27 depict the present invention as an implantable, intraluminal, vascular adapted for use as a implantable multi-leaflet valve 43 including a stent 44 or frame 11 with at least a partial covering 58 .
- the covering comprises a first and a second valve leaflets 78 , 79 that at least partially seal the aperture 56 within the frame 11 while the valve 43 is in the deployed configuration 36 and forms the opening 117 or valve orifice which regulates the flow of fluid 46 , 47 through the valve.
- FIG. 20 shows the device 10 in the first, generally planar configuration 35 where the frame 11 is generally rectangular or in particular square in shape.
- the partial covering 58 forming the leaflets 78 , 79 generally extends across the entire frame 11 with the aperture 56 comprising a slit 108 that extends across the first axis 94 of the frame 11 , the first axis being defined as traversing diagonally opposite bends ( 22 and 23 in this example) that are in line with the valve orifice 117 that forms the valve 43 .
- the covering 45 is therefore divided into at least first and second portions (making it a partial covering 58 ) which define the first and second valve leaflets 78 , 79 .
- a complete covering 45 can be slit open along the axis after it is affixed to the frame, or at least first and second adjacent triangular portions (partial coverings 58 ) can be separately attached, eliminating the need for mechanically forming a slit 108 .
- the slit 108 is made in the covering 45 such that the slit terminates a few millimeters from each of the corner bends 22 , 23 , creating a pair of corner gaps 155 , thereby eliminating two of the most likely sources of leakage around the valve 43 .
- the outer edge 112 of the partial covering 58 that comprises the leaflet 25 is stretched over the frame 11 comprising the valve leg 113 and sutured or otherwise attached as disclosed herein.
- the leaflet 25 is secured in place such that the material is fairly taut, such that when the valve 43 is situated in the vessel 33 and its diameter constrained to slightly less than the valve width 146 , the leaflet 25 assumes a relatively loose configuration that gives it the ability to flex and invert its shape, depending on the direction of fluid flow.
- the inner edge 111 of the leaflet 25 is generally free and unattached to the frame and generally extends between the bends 22 and 23 (the bends 115 of the first end) of the valve leg 113 .
- the inner edge 111 may be reinforced by some means, such as additional material or thin wire, that still would allow it to be sufficiently pliable to be able to seal against another leaflet 25 when retrograde flow 47 forces the leaflets 78 , 79 together.
- the leaflet 25 is sized and shaped such that the inner edge 111 of one leaflet 78 can meet or overlap with the inner edge 111 of the opposing leaflet 79 (or leaflets, e.g., 119 , 120 ), except when degree of normal, positive flow 46 is sufficient to force the leaflets 25 open to permit fluid passage therethrough.
- FIGS. 21-27 are configured into an elongated diamond shape 153 in the planar configuration 35 with the distance between the two bends 22 , 23 aligned with the valve orifice 117 and first axis 94 being less than the distance between bends 20 and 21 along the second, perpendicular axis 95 .
- This diamond configuration 153 can be accomplished by forming the frame 11 into that particular shape, or constraining a square frame into a diamond shape 153 , which will be discussed later.
- the valve legs 127 , 128 become more elongated in shape, which can help add stability when positioning the device 10 during deployment, provides more surface area to receive retrograde flow, and more closely mimics a natural venous valve.
- valve leaflets 78 , 79 are forced apart by the normal pulsatile blood flow 46 ( FIGS. 22,24 ).
- the respective valve leaflets 78 , 79 naturally move back into closer proximity following the pulse of blood.
- Retrograde blood flow 47 forces the valve leaflets 78 , 79 against one another, as depicted in FIGS. 23 and 25 thereby closing off the lumen 34 of the vessel 33 and the valve orifice 117 .
- FIGS. 21A-21B depict embodiments of the valve 43 in which each leaflet 78 , 79 includes a flap 77 of overhanging material along the slit edge 111 to provide advantageous sealing dynamics when the valve 43 is in the deployed configuration 36 as depicted in FIGS. 22-25 .
- the flaps 77 are typically formed by suturing two separate pieces of covering 45 material to the frame such that the inner edge 111 is extendable over the slit 108 and inner edge 111 of the adjacent leaflet 25 . By overlapping with an adjacent flap 77 or leaflet 25 , the flap 77 can provide additional means to help seal the valve orifice 117 . Two embodiments of leaflets 25 with flaps 77 are shown. In FIG.
- the inner edge 111 is basically straight and extends over the first axis 94 of the frame 11 .
- the flaps 77 can be cut to create a corner gap 155 that covers and seals the corner region around the bend 22 , 23 .
- the flap 77 is cut such that there is a notch 157 in the leaflet where the leaflet meets the corner bends 22 , 23 . While these flaps 77 may provide benefit in certain embodiments, the optional flaps 77 shown in FIG. 21 are not necessary to provide a good seal against backflow 47 if the valve 43 and leaflets 25 are properly sized and configured.
- FIGS. 26-26A depict one method of affixing a covering 45 comprising a biomaterial, such as SIS, to the frame 11 which has been constrained using a temporary constraining mechansim 121 , such as a suture, to acheive the desired frame configuration.
- a covering 45 comprising a biomaterial, such as SIS
- the covering 45 is cut larger than the frame 11 such that there is an overhang 80 of material therearound, e.g, 5-10 mm.
- the frame 11 is centered over the covering 45 and the overhang 80 is then folded over from one long side 142 , with the other long side 143 subsequently being folded over the first.
- the covering 45 is sutured to the frame along one side 142 , typically using forceps 158 and needle, thereby enclosing the frame 11 and the coiled eyelet 14 with the overhang 80 along side 142 .
- the covering 45 is sutured to the frame with resorbable or non-resorbable sutures 50 or some other suitable method of attaching two layers of biomaterials can be used.
- a single ply sheet usually about 0.1 mm thick, is used in the hydrated condition.
- 7-0 Prolene suture is used, forming a knot at one bend (e.g., bend 20 ), then continuing to the next bend (e.g., 22 ) with a running suture 50 , penetrating the layers of SIS around the frame at about 1-2 mm intervals with loops formed to hold the suture 50 in place.
- a running suture 50 penetrating the layers of SIS around the frame at about 1-2 mm intervals with loops formed to hold the suture 50 in place.
- the next coil turn 14 is reached, several knots are formed therethrough, and the running suture 50 continues to the next coil turn 14 .
- barbs are present, such as shown in the embodiment of FIG. 21 , the suture 50 is kept inside of the barbs 16 located about each coil turn 14 .
- the covering 45 is affixed to the frame 11 such that one side of the overhang 80 is not sutured over the other side in order to maintain the free edge of the overhang 80 , although the alternative condition would be an acceptable embodiment.
- Alternative attachment methods include, but are not limited to, use of a biological adhesive, a cross-linking agent, heat welding, crimping, and pressure welding.
- synthetic coverings other similar methods of joining or attaching materials are available which are known in the medical arts.
- the covering 45 can be altered in ways that improve its function, for example, by applying a coating of pharmacologically active materials such as heparin or cytokines, providing a thin external cellular layer, e.g., endothelial cells, or adding a hydrophilic material or other treatment to change the surface properties.
- pharmacologically active materials such as heparin or cytokines
- providing a thin external cellular layer e.g., endothelial cells
- a hydrophilic material or other treatment to change the surface properties.
- the overhang 80 is folded back away from the frame, as shown on the second side 143 of the frame of FIG. 26A , and part of the excess overhang 80 is trimmed away with a scalpel 159 or other cutting instrument to leave a 2-4 mm skirt around the frame 11 .
- the overhang 80 or skirt provides a free edge of SIS (or material with similar remodeling properties) to help encourage more rapid cell ingrowth from the vessel wall, such that the SIS replaces native tissue as quickly as possible.
- An unattached edge of the overhang 80 can also form a corner flap 81 or pocket as depicted in FIG. 27 .
- This corner flap 81 can serve to catch retrograde blood flow 47 to provide a better seal between the device 10 and the vessel wall 70 as well as providing an improved substrate for ingrowth of native intimal tissue from the vessel 33 , if made of SIS or another material with remodeling properties.
- the frame 11 used to form the valve 43 embodiments, e.g., FIGS. 20-27 , that are placed in the legs or other deep veins as replacement for incompetent venous valves is sized according to the size of the target vessel.
- a typical venous valve might be made of 0.0075′′ 304 stainless steel mandril wire with an attachment mechanism 15 comprising 23 to 24 gauge thin-wall stainless steel cannula or other tubing. Larger wire (e.g., 0.01′′) and attachment cannula 15 are typically used for valves 43 of the larger diameter (greater than 15 mm). Selection of the attachment cannula 15 depends on competing factors.
- FIG. 30 best depicts an uncovered frame 11 used to form a venous valve 43 , wherein the length of the sides 13 typically range from about 15 to 25 mm.
- heavier gauge wire is typically used.
- 25 mm frames might use 0.01′′ wire, with larger diameter embodiments such as stent occluders used for femoral bypass or stent adaptors, such as shown in FIGS. 17 and 32 , requiring an even heavier gauge.
- the appropriate gauge or thickness of the frame wire also depends on the type of alloy or material used.
- the frame is typically formed in a generally flat configuration and then manipulated into its characteristic serpentine configuration and loaded into a delivery system. Therefore, the frame usually will tend to reassume the first or generally flat configuration if the restraint of the delivery system or vessel is removed. Deformation of the frame 11 can occur after it has been manipulated into the second configuration, however, such that it no longer will lie completely flat, as depicted in FIG. 34 .
- This angle of deformation 129 which varies depending on the frame thickness and material used, generally does not compromise the function of the device 10 , which can be reconfigured into the serpentine configuration (of the second, deployed configurations) without loss of function.
- the frame 11 of the present invention can be made either by forming a series of bends in a length of straight wire and attaching the wire to itself, as previously discussed, to form a closed configuration, or the frame 11 can be formed in the deployment (second) configuration 35 as depicted in FIGS. 41-41A by cutting it out of a flat sheet 152 of material, e.g., stainless steel or nitinol. Further finishing procedures can then be performed after it has been cut or formed, such as polishing, eliminating sharp edges, adding surface treatments or coatings, etc.
- the frame 11 can comprise one or more polymers, composite materials, or other non-metallic materials such as collagen with the frame either being cut from a thin sheet of the material, or molded into the deployment configuration 36 as depicted in FIG. 43 .
- the frame 11 of FIG. 43 does not naturally assume a flattened configuration 35 when the device 10 is unconstrained by the vessel or delivery system.
- FIGS. 41-41A and 43 include integral barbs 124 that extend from the frame 11 , which being formed as a closed frame, does not have free ends 60 , 61 that can be used to serve as barbs 16 as depicted in FIG. 3 and other embodiments.
- FIGS. 41-41A depict a series of integral barbs 124 comprising V-shaped cuts 139 transversing the thickness of the flat metal frame 11 , which are bent outward to form the barb 16 .
- the integral barbs 124 are formed along with the frame 11 with two extending from the frame at either side of each bend 12 .
- These integral barbs 124 can be designed into the mold if the frame 11 is formed out of a polymer material.
- the number, arrangement, and configuration of the integral barbs 124 is generally not critical and can vary according to design preference and the clinical use of the device.
- the barbs 16 may or may not penetrate the covering, depending on their design and other factors, including the thickness and type of covering used.
- the frame embodiment of FIG. 43 can be formed from a variety of medical grade polymers having properties that permit the frame to function as a supporting structure for the valve leaflets 78 , 79 , it should be noted that for some uses, it may be desirable to form the frame 11 from a material that can be degraded and adsorbed by the body over time to advantageously eliminate a frame structure can would remain in the vessel as a foreign body and that could possibly fracture and/or cause perforation of the vessel wall.
- a number of bioabsorbable homopolymers, copolymers, or blends of bioabsorbable polymers are known in the medical arts.
- poly-alpha hydroxy acids such as polyactic acid, polylactide, polyglycolic acid, or polyglycolide; trimethlyene carbonate; polycaprolactone; poly-beta hydroxy acids such as polyhydroxybutyrate or polyhydroxyvalerate; or other polymers such as polyphosphazines, polyorganophosphazines, polyanhydrides, polyesteramides, polyorthoesters, polyethylene oxide, polyester-ethers (e.g., polydioxanone) or polyamino acids (e.g., poly-L-glutamic acid or poly-L-lysine).
- bioabsorbable polymers that may be suitable, including modified polysaccharides such as cellulose, chitin, and dextran or modified proteins such as fibrin and casein.
- FIGS. 44-46 depicts two exemplary embodiments in which the frame 11 is integral with the covering 45 .
- the valve 43 is formed as a single piece of material, such as a flexible polymeric or collagen-based material, whereby there is a thin, compliant central portion comprising the covering 45 or leaflets 78 , 79 , and a thickened edge 141 portion that comprises the frame 11 .
- the valve 43 shown in the generally flat configuration 35 , can be also formed into the deployment configuration 36 (see FIG. 43 ).
- the material of the frame 11 portion can be subjected to treatments or processes that add rigidity or other desired characteristics that permit the frame to better support the covering 45 portion or anchor the device 10 to the vessel wall.
- FIG. 44 depicts two exemplary embodiments in which the frame 11 is integral with the covering 45 .
- the valve 43 is formed as a single piece of material, such as a flexible polymeric or collagen-based material, whereby there is a thin, compliant central portion comprising the covering 45 or leaflets 78 , 79
- intergral barbs 124 can be included along the frame 11 .
- other layers of different materials can be laminated to or blended with the edge portion to provide the desired properties.
- the outside edge 112 of the covering 45 can be folded over itself to form a rolled edge 140 ( FIG. 46 ) that adds rigidity to serve as a frame 11 .
- the rolled edge 140 can be held in placed with a glue, resin, or similar bonding agent 144 .
- the covering 45 and rolled edge 140 can comprise a sheet of SIS with a bonding agent 144 such as collagen glue or other bioabsorbable material used to secure the rolled portion and after hardening, to add the necessary degree of rigidity for the valve 43 (or occluder, filter, stent adaptor, etc.) to assume the deployment configuration within the vessel.
- a bonding agent 144 such as collagen glue or other bioabsorbable material used to secure the rolled portion and after hardening, to add the necessary degree of rigidity for the valve 43 (or occluder, filter, stent adaptor, etc.) to assume the deployment configuration within the vessel.
- a bonding agent 144 such as collagen glue or other bioabsorbable material used to secure the rolled portion and after hardening, to add the necessary degree of rigidity for the valve 43 (or occluder, filter, stent adaptor, etc.) to assume the deployment configuration within the vessel.
- Excess of the bonding agent 144 can be fashioned to structural elements that
- a discernable frame 11 by changing the material or material properties along the outer edge 112 of the leaflets, by adding or incorporating one or more different material or agents along the outer edge 112 of covering 45 such that the stiffness and/or resiliency increased, thereby allowing the frame to hold a desired shape during deployment, while still allowing the adjacent covering material to be sufficiently flexible to function as a leaflet 25 .
- the illustrative valve 43 lacks the radial expandability to anchor itself to the vessel wall, it may be mounted on a balloon to expand the valve 43 and anchor the barbs, if present, into the vessel wall.
- the illustrative embodiments of the present invention generally include a closed frame 11 to give the device 10 its form.
- FIG. 47 depicts an example in which the frame 11 portion is not a closed structure. Rather, a portion of the covering 45 used to span a gap 145 in the frame such that a portion of the outside edge 112 (of leaflet 79 in this example) is unsupported therealong.
- the length of the gaps 145 and their distribution can vary as long as the frame 11 is still able to fulfill its role to support and define the shape of the valve 43 or device 10 .
- FIGS. 21-31 depict various embodiments in which the bends 20 , 21 , 22 , 23 are placed in a resiliently tensioned or stressed state after being initially formed such that the bends were not under tension.
- the addition of tension to one or more bends 12 of the device frame 11 can alter the properties of the frame 11 and result in improved sealing characteristics or the ability of the device 10 to impinge upon the vessel wall 70 to prevent migration or shifting.
- the coil turn 14 is formed as previously disclosed whereby each bend 12 is in a untensioned state with the adjacent sides 13 having an initial angle after formation of the bend 12 .
- the initial angle 109 after the bends are formed and the final angle 110 after the frame 11 is assembled are both approximately 90 ⁇ . Therefore, the bends 12 of the embodiment of FIG. 20 are not placed under any significant degree of tension.
- the frame is restrained to permanently place the bends 12 under tension such that the angle between the sides 122 , 123 adjacent to the bend 12 is increased or decreased by some method of manipulation to produce a resiliently tensioned bend 118 ( FIGS. 26 and 29 ) having a final angle 110 different than the initial angle 109 (e.g., FIG. 28 ).
- the covering 45 (including a full or a partial covering 58 ) can be attached to the frame 11 of the valve 43 or other embodiment of the present invention, to constrain a generally untensioned square frame 11 (such as in FIG. 1 ) and subsequently form an altered shape 82 , such as a diamond 153 , in which the distance between bends 20 and 21 is lengthened and the distance between bends 22 and 23 is shortened.
- an altered shape 82 such as a diamond 153
- the angle 110 measured between the adjacent sides 13 from bends 20 and 21 might decrease to 70-80 ⁇ with a increase in the corresponding angles 161 measured at bends 22 and 23 to 100-110 ⁇ .
- This manipulation of the frame 11 shape serves to add tension in each of the bends, which allows better positioning of the device 10 against the vessel wall 70 while in the deployed configuration, as shown in FIGS. 22-25 . Additionally, constraining the frame 11 along the first axis 94 of the slit 108 allows that distance 146 to be adjusted to provide the optimum size for the vessel 33 into which the valve 43 is to be implanted.
- the leaflets 25 should ideally span about 30-60% of the vessel 33 diameter across. If it is much less than 30%, blood flow 46 may be impeded to an unacceptable degree, while if the leaflets 78 , 79 are allowed to fully open, they can adhere to the vessel wall 70 and therefore, not close properly in the presence of retrograde flow 47 .
- the frame 11 can be formed or constrained such that the distance 146 between points 22 , 23 lies between ⁇ r, which would allow the valve to open to the full extent that the vessel allows, and 2 r in which the valve 43 is stretched tight across the frame 11 and is very limited in the amount of blood that will allow to pass through.
- the slit axis distance 146 of the valve 43 should be oversized with respect to the diameter of the vessel into which it is to be placed.
- FIG. 49 depicts a schematic top view of the valve of FIG.
- the preceding formula can be used to determine the amount of oversize that produces the desired characteristics.
- the amount of oversize (valve width 146 in the flat configuration minus the diameter of the vessel lumen 34 ) would generally range from 1-2 mm for smaller valves (those placed in 8-9 mm vessels) up to 3-4 mm for valves intended for larger vessels (17-21 mm).
- a valve intended for a 14 mm vessel should ideally have a 2-3 mm oversize if the range of 30-60% opening is to be maintained.
- valve 43 If the frame 11 of a valve 43 having 20 mm sides is constrained such that the distance between bends 22 and 23 is adjusted to approximately 16 mm, the valve 43 opens approximately 43%, which is well within the most desired range. If constrained to 17 mm, the valve 43 is able to open up to approximately 55% of the vessel diameter. In contrast, oversizing the valve 43 by 6 mm, produces a large orifice 117 of 83% which lies outside the target range, although it would certainly produce a valve 43 capable of opening and closing in response to fluid flow 46 , 47 .
- the 20 mm frame 11 should be constrained such that the distance between bends 22 and 23 is 15 mm prior to addition of the covering 45 , if a compliant material such as SIS is used.
- a compliant material such as SIS is used.
- the frame 11 is constrained across the first axis 94 using a temporary constraining mechanism 121 , such as by tying a suture through the coil turns 14 of bends 22 and 23 to pull them toward one another until a distance of 15 mm is reached.
- the temporary constraining suture 121 is cut, which results in a slight expansion in the width of the frame 11 as the SIS stretches under the tension of the constrained frame, resulting in the desired final width of 17-18 mm.
- the amount of expansion varies with the compliance of the particular covering 45 as well as the resiliency of the frame 11 .
- the desired final width 146 of the constrained frame 11 can result from a relatively wide range of initial frame 11 sizes, depending on how much the frame is constrained, generally, larger sized frames (e.g., sides measuring about 25 mm) are most suitable for larger vessels (e.g., 16-21 mm in diameter), while smaller frames (e.g., 15 mm) are most suitable for smaller diameter vessels (e.g., 8-9 mm). While this range represents the most common sizes used for correcting venous valve insufficiency in the lower legs, valves 43 of the present invention can be made in a much larger range of sizes to treat veins or other vessels elsewhere in the body.
- FIGS. 28-31 depict another embodiment of the present invention in which a open frame 11 , such as depicted in FIG. 28 , is assembled into a square frame ( FIGS. 29-31 ) such the bends 12 are put under tension.
- the resiliently tensioned bends 118 in the assembled device result from the initial angle 109 formed in wire frame 11 before being assembled into a closed circumference 62 ( FIG. 28 ), being greater than the final angle 110 .
- the wire is wrapped around a pin to form the coil turns 14 with the sides 13 generally lying about 90 ⁇ with respect to one another.
- the attachment mechanism 15 then secures and closes the frame 11 to form the final square shape.
- the first angle 109 is made approximately 150 ⁇ , rather than 90 ⁇ , which is the desired final angle 110 .
- the bends 12 and sides 13 are stressed when the device 10 is constrained during assembly to form the four-sided, generally square shape.
- the sides 122 , 123 adjacent to a resiliently tensioned bend 118 becomes somewhat deformed when the bend 12 is put under stress, generally assuming a bowed shape between the adjacent bends.
- the sides 13 of the frame 11 are able to better conform to the rounded vessel wall 70 than would a side 13 that is initially straight prior to deployment. Additionally, by rounding the distal bends 116 of the valve legs 113 , it may also reduce the potential for the valve legs 113 to cause trauma to the vessel 33 as they continue to exert force thereupon.
- FIG. 48 An additional method of constraining the valve 43 , or similar type device 10 (e.g., occluder, filter, stent, stent adaptor), is depicted in FIG. 48 in which a circumferentially constraining mechanism 125 , is added to at least partially encircle the frame 11 while it is in both the delivery configuration 37 ( FIG. 6 ) and the deployed configuration 36 such that the device 10 is limited in its ability to radially expand. Once the device reaches its maximal radial expansion, the outward force the device 10 places on the vessel wall 70 is eliminated, thereby reducing potential damage thereto (e.g., from an improperly sized valve), such as tissue erosion possibly resulting in eventual perforation of the vessel 33 .
- potential damage thereto e.g., from an improperly sized valve
- the circumferentially constraining mechanism 125 comprises a suture that is affixed to and completely encircles the frame 11 to limit the outward expansion of the valve legs 127 , 128 .
- the sides 13 of the valve legs 127 , 128 include an intermediate coil turn 126 , also illustrated in FIG. 39 fulfilling a different function, that provides an effective attachment point through which to feed and/or affix the suture restraint 125 .
- the suture restraint 125 is in a relaxed state when the device 10 is loaded in the delivery system.
- the device 10 expands within the vessel 33 until it is constrained by the suture restraint 125 if the device 10 has been properly sized such that vessel 33 does not provide constraining forces sufficient to prevent the device 10 from fully expanding to its predetermined maximum diameter. If the device is undersized for the diameter of the vessel, it may be subject to migration due to insufficient expansion.
- the illustrative embodiment is merely exemplary of the numerous available circumferentially constraining mechanisms 125 . It is not necessary that the circumferentially constraining mechanism 125 completely encircle the device 10 .
- short pieces of suture or another type of tethering mechanism can be affixed between the sides of the valve legs to limit their expansion
- the frame can include an integral circumferentially constraining mechanism, such as an expandable strut formed as part of the frame.
- the strut would unfold as the frame radially expands and limits how far the sides of the valve leg to which is attached, can spread apart relative to each other, thereby limiting the outward radial force from the device against the vessel wall.
- circumferentially constraining mechanism 125 to comprise a sleeve 162 of flexible material, such as SIS around the valve 43 , as depicted in FIG. 50 , which is of a diameter appropriate for deployment within the target vessel 33 (typically, being slightly larger than the target vessel diameter) that allows the valve to anchor thereto.
- the sleeve 162 could be affixed to the frame 11 with sutures 50 or by some other means as the valve 43 is held in a collapsed condition prior to loading the device 10 , including the sleeve 162 , into a delivery system.
- the sleeve 162 enclosed the length of the valve 43 , or the bends 12 and barbs 16 can be left uncovered, as shown.
- tethers and other types of circumferentially constraining mechanism 125 can be used in combination with the sleeve 162 to limit radial expandability of the valve 43 . It should be noted that if the circumferentially constraining mechanism 125 itself is a resilient member, it will only serve to reduce the outward force of the device 10 against the vessel wall 70 until maximum expansion is reached.
- FIGS. 30-31 depict alternative methods of forming the frame 11 and attaching barbs thereto.
- attachment mechanisms 15 , 85 and 84 , 86 per side rather than a single cannula as shown in previous embodiments, such as FIG. 29 .
- two attachment mechanisms 15 , 85 are placed on either side of the cross point 87 .
- Having an additional attachment mechanism 84 , 85 , 86 on a side 13 provides better fixation of the frame with little additional metal and helps prevent twisting of the frame 11 .
- the double attachment mechanisms 84 , 86 arrangement provides a similar function.
- three attachment mechanisms 15 , 85 , 88 and 84 , 86 , 89 are used per side which provide better fixation of the frame 11 as well as serving as attachment points for including supplemental barbs 90 , 91 , 92 , 93 to provide a more secure anchoring of the device 10 to the vessel wall 70 .
- the illustrative barbs 16 are typically configured such that they extend only a short distance (less than 1-2 mm) beyond the bends 12 ; however, the barbs 16 can be made virtually any practical length, such as extending them more than 1 cm beyond the bends 12 to aid in stabilizing the device 10 upon deployment such that it does not shift laterally and end up being cockeyed within the vessel. To assist in this function, the barbs can be shaped accordingly, rather than be limited to a substantially straight configuration.
- FIGS. 35-40 depict multi-leaflet valves 43 having three or four valve legs 113 and leaflets 25 .
- the addition of additional leaflets reduces the load produced by the fluid column upon each individual leaflet 25 . This in turn, puts less stress upon the sutures or attachment points of the covering 45 , thereby allowing the valve 43 to function under higher pressures than would otherwise be possible.
- these valves 43 could prove advantageous for use on the arterial side, such as to augment pulmonary valves, or within the heart itself, where pressures exerted on the leaflets can be significantly higher than normally found on the venous side.
- valve 35 depicts a valve 43 which in the generally flattened configuration 35 , has a three legs 127 , 128 , 130 that lie approximately 120 ⁇ with respect to one another.
- the respective leaflets are arranged such that the inner edges 111 thereof, define a triangular-shaped valve orifice 117 .
- the leaflets 78 , 79 , 119 are able to close against one another to seal the valve.
- the concept of adding additional legs 113 to distribute the load over a larger number of attachment points 50 (e.g., sutures) and add positional stability to the device 10 can be applied to occluders and stent adaptors as well.
- One method of forming the embodiment of FIG. 35 involves constructing a triangular-shaped frame 1 , as shown in FIG. 36 , that includes an intermediate coiled eyelet 132 formed at the midpoint of each of the three sides 13 .
- a temporary constraining suture 121 such as that shown in FIG. 38 , is threaded through each of the intermediate eyelets 132 , drawing them inward to form three additional bends 133 , 134 , 135 forming three legs 127 , 128 , 130 of a desired shape ( FIG. 35 ), depending how tightly the constraining suture 121 is drawn.
- the covering 45 is attached to the frame 11 , either as three separate leaflets 78 , 79 , 119 , or a single piece through which the triangular-shaped valve orifice 117 is formed.
- the constraining suture 121 is cut and removed.
- the barbs 16 are affixed to the triangular shaped frame of FIG. 36 , two per side, such that they terminate on either side of intermediate eyelet 132 .
- FIGS. 38-40 which includes four legs 127 , 128 , 130 , 131 , is formed in a similar manner to that of the embodiment of FIGS. 35-37 .
- the frame 11 is initially formed in a square configuration ( FIG. 39 ) with intermediately placed coiled eyelets 132 at the midpoint of each side 13 , dividing the side into a first and second side portion 137 , 138 . As depicted in FIG.
- the temporary constraining suture 121 is used to draw the eyelets inward where they form the four additional bends 133 , 134 , 135 , 136 such that four valve legs 127 , 128 , 130 , 131 are formed with the first and second sides portions 137 , 138 becoming sides 13 of adjacent valve legs 127 , 128 .
- a square-shaped valve orifice 117 is created when the four leaflets 78 , 79 , 119 , 120 are attached to the legs 127 , 128 , 130 , 131 of frame 11 .
- valves with more than four legs would be made in a similar manner to the embodiments above with a five-sided valve being formed from a pentagon, a six-sided valve being formed from a hexagon, etc.
- Delivery of the device 10 of the present invention can be accomplished in a variety of ways.
- One method depicted in FIG. 33 , involves the use of a delivery system 103 similar to that used to deliver embolization coils.
- the delivery system 103 comprises an outer member 105 , such as a cannula or catheter, and an coaxial inner member 105 that includes a tethering tip 107 , such as a notched cannula, adapted to receive a barb 17 extending from the frame 11 .
- the tip 104 of the barb is configured such that it can positively engage with the tethering tip 107 . This can be accomplished by adding a projection, such as a secondary barb, hook, spine, etc.
- the coaxial inner member 106 also includes an outer sheath 149 that retains and the locks the barb tip 104 within the tethering tip 107 until it is advanced or retracted by manipulation of a proximal handle (not shown) to expose the notch 150 in the tethering tip, which releases the barb 17 and deploys the device 10 .
- the device 10 is preloaded within the outer member 105 .
- the coaxial inner member 106 and attached device 10 are then advanced together from the outer member 106 at the target site.
- the tethering tip 107 which in this particular embodiment, includes a coiled spring 151 , relative to the outer sheath 149 .
- the spring-activated handle is released and the outer sheath 149 slides back over the tethering tip 107 .
- the coaxial inner member 106 is withdrawn into the outer member 105 and the entire delivery system 103 is removed from the patient.
- the barb tip 104 extends just beyond the coil turn 14 of the frame 11 so as to have sufficient room to engage with the coaxial inner member 106 .
- the barb tip 104 must be positioned to account for whether the device 10 is to be placed using a femoral approach or a superior approach.
- the illustrative delivery system 103 represents only one of many possibilities.
- the device 10 can be attached to a delivery device using screws, clips, magnets, or some other tethering mechanism, or can be deployed by applying electrical current, heat, or some other means to cause detachment with a carrying mechanism.
- the device 10 can be formed from a ductile material, mounted over a balloon or other inflatable or expandable delivery mechanism, and deployed by expanding the device in that manner.
- the present invention includes devices having a number of configurations with regard to the frame, covering, barbs, etc. Futhermore, it has been seen that the invention and can be formed in a variety of ways using a different types of medical grade materials, and has utility to treat a wide range of medical problems.
- the embodiments contained herein should be considered merely exemplary as one skilled in the medical arts would appreciate that further modifications would be possible that would be included within the spirit of the invention.
Abstract
Description
- This application is a continuation of, and fully incorporates by reference, U.S. utility patent application Ser. No. 09/777,091, filed Feb. 5, 2001, published as U.S. 2001-0039450 A1 on Nov. 8, 2001, which claims priority to Provisional U.S. Patent Application Ser. No. 60/180,002, filed Feb. 3, 2000 and regular utility application Ser. No. 09/324,382, filed Jun. 2, 1999, and issued as U.S. Pat. No. 6,200,336 on Mar. 13, 2001.
- 1. Technical Field
- This invention relates to medical devices, more particularly, to intraluminal devices.
- 2. Background Information
- As minimally invasive techniques and instruments for placement of intraluminal devices have developed over recent years, the number and types of treatment devices have proliferated as well. Stents, stent grafts, occlusion devices, artificial valves, shunts, etc., have provided successful treatment for a number of conditions that heretofore required surgery or lacked an adequate solution altogether. Minimally invasive intravascular devices especially have become popular with the introduction of coronary stents to the U.S. market in the early 1990s. Coronary and peripheral stents have been proven to provide a superior means of maintaining vessel patency. In addition, they have subsequently been used as filter, occluders, or in conjunction with grafts as a repair for abdominal aortic aneurysm, with fibers or other materials as occlusion devices, and as an intraluminal support for artificial valves, among other uses.
- Some of the chief goals in designing stents and related devices include providing sufficient radial strength to supply sufficient force to the vessel and prevent device migration. An additional concern in peripheral use, is having a stent that is resistant to external compression. Self-expanding stents are superior in this regard to balloon expandable stents which are more popular for coronary use. The challenge is designing a device that can be delivered intraluminally to the target, while still being capable of adequate expansion. Self-expanding stents usually require larger struts than balloon expandable stents, thus increasing their profile. When used with fabric or other coverings that require being folded for placement into a delivery catheter, the problem is compounded.
- There exists a need to have a basic stent, including a fabric or biomaterial covering, that is capable of being delivered with a low profile, while still having a sufficient expansion ratio to permit implantation in larger vessels, if desired, while being stable, self-centering, and capable of conforming to the shape of the vessel. There is a further need to have a intraluminal valve that can be deployed in vessels to replace or augment incompetent native valves, such as in the lower extremity venous system to treat patients with venous valve insufficiency. Such a valve should closely simulate the normal functioning valve and be capable of permanent implantation with excellent biocompatibility.
- The foregoing problems are solved and a technical advance is achieved in an illustrative implantable valve that is deployed within a bodily passage, such as a blood vessel or the heart, to regulate or augment the normal flow of blood or other bodily fluids. The valve includes a covering having oppositely facing curvilinear-shaped surfaces (upper and lower) against which fluid traveling in a first or second direction within the bodily passage exerts force to at least partially open or close the valve. At least one outer edge of the covering resiliently engages and exerts force against the wall of the vessel and has arcuate shape that provides at least a partial seal against the wall.
- In one aspect of the invention, the covering comprises a plurality of leaflets, each leaflet having a body extending from a wall-engaging outer edge to a free edge which is cooperable with one or more opposing leaflets to prevent flow in one direction, such as retrograde flow, while at least a portion of the leaflets having sufficient flexibility, when in situ to move apart, thereby creating a valve orifice that permits flow in the opposite direction, such as normal blood flow. The outer edge of each leaflet is adapted to engage and resilient exert force against a wall of the bodily passage such that it extends in both a longitudinal and circumferential directions along the vessel wall to at least partially seal a portion of the vessel lumen, while the free edge of each leaflet traverses the passageway across the diameter of the vessel.
- In another aspect of the invention, the valve includes a frame that is covered by a piece of biocompatible material, preferably an Extracellular Collagen Matrix (ECM) such as small intestinal submucosa (SIS) or another type of submucosal-derived tissue. Other potential biomaterials include allographs such as harvested native valve tissue. The material is slit or otherwise provided with an opening along one axis to form two triangular valve leaflets over a four-sided frame. In the deployed configuration, the leaflets are forced open by normal blood flow and subsequently close together in the presence of backflow to help eliminate reflux. Other configurations include a two-leaflet valve having an oval or elliptically shaped frame, and valves having three or more legs and associated leaflets, which provide a better distribution of the load exerted by the column of fluid acting on the leaflets.
- In still another aspect of the invention, the frame of the device is modified by placing one or more of the bends under tension which results in the frame assuming a second shape that has superior characteristics of placement within the vessel. One method of adjusting the shape includes forming the bends in the wire at an initial angle, e.g., 150□, that is larger than the desired final angle, e.g., 90□ for a four-sided valve, so when the frame is constrained into the final configuration, the sides are arcuate and bow outward slightly. The curvature of the sides allows the sides to better conform to the rounded countours of the vessel wall when the valve is deployed. In devices having a full or partial covering of material over the frame, a second method of modifying the shape is to use the material to constrain the frame in one axis. One such embodiment includes a four-sided valve with two triangular-shaped halves of material, such as SIS, where the material constrains the frame in a diamond shape. This puts the bend of the frame under stress or tension which permits better positioning within the vessel. It also allows the diagonal axis of the frame with the slit or orifice to be adjusted to the optimal length to properly size the frame for the vessel such that the leaflets open to allow sufficient flow, but do not open to such a degree that they contact the vessel wall. The potential benefits of both adding tension to the bends to bow the sides and constraining the frame into a diamond shape using the covering, can be combined in a single embodiment or employed separately.
- In still another aspect of the present invention, the device includes a frame that in one embodiment, is formed from a single piece of wire or other material having a plurality of sides and bends each interconnecting adjacent sides. The bends can be coils, fillets, or other configurations to reduce stress and improve fatigue properties. The single piece of wire is preferably joined by an attachment mechanism, such as a piece of cannula and solder, to form a closed circumference frame. The device has a first configuration wherein the sides and bends generally lie within a single, flat plane. In an embodiment having four equal sides, the frame is folded into a second configuration where opposite bends are brought in closer proximity to one another toward one end of the device, while the other opposite ends are folded in closer proximity together toward the opposite end of the device. In the second configuration, the device becomes a self-expanding stent. In a third configuration, the device is compressed into a delivery device, such as a catheter, such that the sides are generally beside one another. While the preferred embodiment is four-sided, other polygonal shapes can be used as well. The frame can either be formed into a generally flat configuration, or into the serpentine configuration for deployment. Besides rounded wire, the frame can comprise wires of other cross-sectional shapes (e.g., oval, delta, D-shape), or flat wire. Additionally, the frame can be molded from a polymer or composite material, or formed from a bioabsorbable material such as polyglycolic acid and materials with similar properties. Another method is to laser cut the frame out of a metal tube, such as stainless steel or nitinol. Still yet another method is to spot weld together, or otherwise attach, a series of separate struts that become the sides of a closed frame. In further alternative embodiments, the frame can be left with one or more open gaps that are bridged by the material stretched over the remainder of the frame. The frame can also be formed integrally with the covering, typically as a thickened or strengthened edge portion that gives the device sufficient rigidity to allow it to assume the deployed configuration in the vessel. To prevent the frame from radially expanding within the vessel beyond the point which would be considered safe or desirable, the device can be formed into the serpentine configuration and a circumferentially constraining mechanism, such as a tether, strut, sleeve, etc., placed around the device, or built into the frame, to expand or unfold during deployment of the device to limit its expansion to a given diameter, such as that which is slightly larger than the vessel into which it is placed to allow anchoring, but not permit the device to exert to great a force on the vessel wall.
- In another aspect of the present invention, one or more barbs can be attached to the frame for anchoring the device in the lumen of a vessel. The barbs can be extensions of the single piece of wire or other material comprising the frame, or they can represent a second piece of material that is separately attached to the frame by a separate attachment mechanism. An elongated barb can be used to connect additional devices with the second and subsequent frames attached to the barb in a similar manner. Additional barbs can be secured to the device from cannulae placed over the frame. In embodiments in which the frame is formed as a single piece, such as when cut from a sheet of material or injection molded, the barbs can be formed as integral extensions of the frame.
- In still another aspect of the present invention, a covering, which can be a flexible synthetic material such as DACRON, or expanded polytetrafluorethylene (ePTFE), or a natural or collagen-based material, such as an allographic tissue (such as valvular material) or a xenographic implant (such as SIS), can be attached to the device with sutures or other means to partially, completely, or selectively restrict fluid flow. When the covering extends over the entire aperture of the frame, the frame formed into the second configuration functions as an vascular occlusion device that once deployed, is capable of almost immediately occluding an artery. An artificial valve, such as that used in the lower legs and feet to correct incompetent veins, can be made by covering half of the frame aperture with a triangular piece of material. The artificial valve traps retrograde blood flow and seals the lumen, while normal blood flow is permitted to travel through the device. In related embodiments, the device can be used to form a stent graft for repairing damaged or diseased vessels. In a first stent graft embodiment, a pair of covered frames or stent adaptors are used to secure a tubular graft prosthesis at either end and seal the vessel. Each stent adaptor has an opening through which the graft prosthesis is placed and an elongated barb is attached to both frames. In another stent graft embodiment, one or more frames in the second configuration are used inside a sleeve to secure the device to a vessel wall.
-
FIG. 1 depicts a top view of one exemplary embodiment of the present invention; -
FIG. 2 depicts a pictorial view of the embodiment ofFIG. 1 ; -
FIGS. 3, 3A and 3B depict a top view and enlarged, partial cross-sectional views of a second exemplary embodiment of the present invention; -
FIG. 4 depicts a side view of the embodiment ofFIG. 3 deployed in a vessel; -
FIG. 5 depicts a enlarged partial view of the embodiment ofFIG. 1 ; -
FIG. 6 depicts a partially-sectioned side view of the embodiment ofFIG. 1 inside a delivery system; -
FIG. 7 depicts a top view of a third embodiment of the present invention; -
FIG. 8 depicts a side view of the embodiment ofFIG. 7 deployed in a vessel; -
FIGS. 9, 10 and 11 depict enlarged partial views of other embodiments of the present invention; -
FIG. 12 depicts a top view of a fourth embodiment of the present invention; -
FIGS. 13 and 14 depicts side views of the embodiment ofFIG. 12 ; -
FIG. 15 depicts a top view of a fifth embodiment of the present invention; -
FIG. 16 depicts a side view of the embodiment ofFIG. 15 ; -
FIG. 17 depicts a side view of a sixth embodiment of the present invention; -
FIG. 18 depicts an enlarged pictorial view of a seventh embodiment of the present invention; -
FIG. 19 depicts a top view of an eighth embodiment of the present invention; -
FIG. 20 depicts a top view of a first embodiment of a multi-leaflet intraluminal valve of the present invention; -
FIG. 21 depicts a top view of a second embodiment of a multi-leaflet intraluminal valve; -
FIG. 21A depicts a partial top view of another embodiment of leaflets of the present invention; -
FIG. 21B depicts a top view of another embodiment of leaflet of the present invention; -
FIGS. 22 and 23 depict side views of the embodiment ofFIG. 21 when deployed in a vessel; -
FIGS. 24 and 25 depict pictorial views of the embodiments ofFIG. 21 when deployed in a vessel; -
FIGS. 26 and 26 A depict the method of attaching the covering to the embodiment ofFIG. 21 ; -
FIG. 27 depicts a pictorial view of the basic valve ofFIG. 21 upon deployment with an alternative leaflet embodiment; -
FIGS. 28, 29 , 30 and 31 depict top views of selected embodiments of the present invention, made using the method shown inFIG. 28 ; -
FIG. 32 depicts a pictorial view of an embodiment of a stent graft that includes stent adaptors of the present invention; -
FIG. 33 depicts a delivery system for deploying an embodiment of the present invention; and -
FIG. 34 depicts a pictorial view of the present invention having returned to the first configuration following formation into the second configuration; -
FIGS. 35 and 36 depict top views of a three-leg valve embodiment of the present invention, before and after being constrained; -
FIG. 37 depicts a pictorial view of the embodiment ofFIG. 35 in the deployed configuration; -
FIGS. 38 and 39 depict top views of four-leg valve embodiments of the present invention, before and after being constrained; -
FIG. 40 depicts a pictorial view of the embodiment ofFIG. 38 in the deployed configuration; -
FIG. 41 depicts a top view of a frame formed from a sheet of material; -
FIG. 41A depicts a detail view of the embodiment ofFIG. 41 ; -
FIG. 42 depicts a top view of a third embodiment of an intraluminal valve; -
FIG. 43 depicts a pictorial view a frame embodiment formed into a deployed configuration; -
FIG. 44 depicts a top view of an embodiment of implantable valve having an integrally formed frame and covering; -
FIG. 45 depicts a cross-sectional view taken along line 45-45 ofFIG. 44 ; -
FIG. 46 depicts a cross-sectional view of a second embodiment of valve having an integrally formed frame and covering; -
FIG. 47 depicts a top view of an intraluminal valve embodiment having an open frame; -
FIGS. 48 and 49 depict a pictorial views of an intraluminal valve embodiments that includes a circumferentially constraining mechanism; and -
FIG. 50 depicts a top view of the embodiment ofFIG. 22 . - The invention is further illustrated by the following (preceding) pictorial embodiments, which in no way should be construed as further limiting. The present invention specifically contemplates other embodiments not illustrated but intended to be included in the appended claims. FIGS. 1-11,18-19 are directed to a basic stent frame;
FIGS. 12-14 are directed to a single-leaflet valve;FIGS. 15-16 are directed to an occluder (or filter);FIGS. 17 and 32 are directed to a stent adaptor for a stent graft,FIG. 20-27 , 35-40, 42-50 are directed to a multi-leaf valve; andFIG. 28-31 are directed to a constrained frame which can be used to form any of the other embodiments. -
FIG. 1 depicts a top view of one embodiment of themedical device 10 of the present invention comprising aframe 11 of resilient material, preferably metal wire made of stainless steel or a superelastic alloy (e.g., nitinol). While round wire is depicted in each of the embodiments shown herein, other types, e.g., flat, square, triangular, D-shaped, delta-shaped, etc. may be used to form the frame. In the illustrative embodiment, the frame comprises aclosed circumference 62 of asingle piece 59 of material that is formed into adevice 10 having a plurality ofsides 13 interconnected by a series ofbends 12. The depicted embodiment includes foursides 13 of approximately equal length. Alternative embodiments include forming a frame into any polygonal shape, for example a pentagon, hexagon, octagon, etc. One alternative embodiment is shown inFIG. 19 that includes a four-sided frame 11 having the general shape of a kite with two adjacentlonger sides 66 and two adjacent shorter sides 67. In the embodiment ofFIG. 1 , thebends 12 interconnecting thesides 13 comprise acoil 14 of approximately one and a quarter turns. The coil bend produces superior bending fatigue characteristics than that of asimple bend 40, as shown inFIG. 9 , when the frame is formed from stainless steel and most other standard materials. The embodiment ofFIG. 9 may be more appropriate, however, if the frame is formed from nitinol (NiTi) or other superelastic alloys, as forming certain type of bends, such ascoil 14, may actually decrease fatigue life of a device of superelastic materials. Therefore, thebend 12 should be of a structure that minimizes bending fatigue.Alternative bend 12 embodiments include an outward-projectingfillet 41 as shown inFIG. 10 , and an inward-projectingfillet 42 comprising a series ofcurves 63, as shown inFIG. 11 . Fillets are well known in the stent art as a means to reduce stresses in bends. By having the fillet extend inward as depicted inFIG. 11 , there is less potential trauma to the vessel wall. - When using stainless steel wire, the size of the wire which should be selected depends on the size of device and the application. An occlusion device, for example, preferably uses 0.010″ wire for a 10 mm square frame, while 0.014″ and 0.016″ wire would be used for 20 mm and 30 mm frames, respectively. Wire that is too stiff can damage the vessel, not conform well to the vessel wall, and increase the profile of the device when loaded in the delivery system prior to deployment.
- Returning to
FIG. 1 , thesingle piece 59 of material comprising theframe 11 is formed into theclosed circumference 62 by securing the first and second ends 60,61 with anattachment mechanism 15 such as a piece of metal cannula. The ends 60,61 of thesingle piece 59 are then inserted into thecannula 15 and secured withsolder 25, a weld, adhesive, or crimping to form theclosed frame 11. The ends 60,61 of thesingle piece 59 can be joined directly without addition of acannula 15, such as by soldering, welding, or other methods to join ends 61 and 62. Besides joining the wire, the frame could be fabricated as a single piece ofmaterial 59, by stamping or cutting theframe 11 from another sheet (e.g., with a laser), fabricating from a mold, or some similar method of producing a unitary frame. - The
device 10 depicted inFIG. 1 is shown in itsfirst configuration 35 whereby all fourbends sides 13 generally lie within a single flat plane. To resiliently reshape thedevice 10 into asecond configuration 36, shown inFIG. 2 , theframe 11 ofFIG. 1 is folded twice, first along onediagonal axis 94 withopposite bends opposite bends second configuration 36, depicted inFIG. 2 , has twoopposite bends first end 68 of thedevice 10, while the other opposite bends 22,23 are oriented at thesecond end 69 of thedevice 10 and rotated approximately 90□ with respect tobends second configuration 36 can be used as astent 44 to maintain anopen lumen 34 in avessel 33, such as a vein, artery, or duct. The bending stresses introduced to theframe 11 by the first and second folds required to form thedevice 10 into thesecond configuration 36, apply force radially outward against thevessel wall 70 to hold thedevice 10 in place and prevent vessel closure. Absent any significant plastic deformation occurring during folding and deployment, the device in thesecond configuration 36 when not with the vessel or other constraining means, will at least partially return to thefirst configuration 25, although some deformation can occur as depicted inFIG. 34 , depending on the material used. It is possible to plastically form the stent into this configuration which represents an intermediate condition between the first configuration (which it also can obtain) and the second configuration. It is also possible to plastically deform thedevice 10 into thesecond configuration 36, such that it does not unfold when restraint is removed. This might be particularly desired if the device is made from nitinol or a superelastic alloy. - The standard method of deploying the
medical device 10 in avessel 33, depicted inFIG. 6 , involves resiliently forming theframe 11 into athird configuration 37 to load into adelivery device 26, such as a catheter. In thethird configuration 37 theadjacent sides 13 are generally beside each other in close proximity extending generally along the same axis. To advance and deploy the device from thedistal end 28 of thedelivery catheter 26, apusher 27 is placed into thecatheter lumen 29. When thedevice 10 is fully deployed, it assumes thesecond configuration 36 within the vessel as depicted inFIG. 2 . Thesides 13 of the frame, being made of resilient material, conform to the shape of thevessel wall 70 such that when viewed on end, thedevice 10 has a circular appearance when deployed in a round vessel. As a result, sides 13 are arcuate or slightly bowed out to better conform to the vessel wall. - A second embodiment of the present invention is depicted in
FIG. 3 wherein one ormore barbs 16 are included to anchor thedevice 10 following deployment. As understood, a barb can be a wire, hook, or any structure attached to the frame and so configured as to be able to anchor thedevice 10 within a lumen. The illustrative embodiment includes afirst barb 16 with up to threeother barbs FIG. 3 , thebarb combination 38 that comprisesbarbs single piece 59 of material of theframe 11 beyond theclosed circumference 59. Theattachment cannula 15 secures and closes thesingle piece 59 of material into theframe 11 as previously described, while the first and second ends 60,61 thereof, extend from thecannula 15, running generally parallel with theside 13 of theframe 11 from which they extend, each preferably terminating around or slightly beyondrespective bends distal end 19 of thebarb 16 in the illustrative embodiment contains a bend or hook. - Optionally, the tip of the
distal end 19 can be ground to a sharpened point for better tissue penetration. To add a third and fourth barb as shown, a double endedbarb 39 comprisingbarbs opposite side 13 as defined bybends barb combination 38, thedouble barb 39, as shown in detail view B ofFIG. 3 , comprises a piece of wire, usually the length ofbarb combination 38, that is separate from thesingle piece 59 comprising themain frame 11. It is secured to the frame byattachment mechanism 15 using the methods described forFIG. 1 .FIG. 4 depicts barb 17 (and 18) engaging thevessel wall 70 while thedevice 10 is in the second, deployedconfiguration 36. While this embodiment describes up to a four barb system, more than four can be used. -
FIG. 7 depicts a top view of a third embodiment of the present invention in thefirst configuration 35 that includes a plurality offrames 11 attached in series. In the illustrative embodiment, afirst frame 30 andsecond frame 31 are attached by abarb 16 that is secured to each frame by theirrespective attachment mechanisms 15. Thebarb 16 can be a double-endedbarb 39 as shown inFIG. 3 (and detail view B) that is separate from thesingle pieces 59 comprisingframes single pieces 59 as shown in detail view A ofFIG. 3 . Further frames, such asthird frame 32 shown in dashed lines, can be added by merely extending the length of thebarb 16.FIG. 8 depicts a side view of the embodiment ofFIG. 7 in thesecond configuration 36 as deployed in avessel 33. -
FIGS. 12-18 depict embodiments of the present invention in which a covering 45 comprising a sheet of fabric, collagen (such as small intestinal submucosa), or other flexible material is attached to theframe 11 by means ofsutures 50, adhesive, heat sealing, A weaving@ together, crosslinking, or other known means.FIG. 12 depicts a top view of a fourth embodiment of the present invention while in thefirst configuration 35, in which the covering 45 is apartial covering 58, triangular in shape, that extends over approximately half of theaperture 56 of theframe 11. When formed into thesecond configuration 36 as shown inFIGS. 13-14 , thedevice 10 can act as anartificial valve 43 such as the type used to correct valvular incompetence.FIG. 13 depicts thevalve 43 in theopen configuration 48. In this state, thepartial covering 58 has been displaced toward thevessel wall 70 due to positive fluid pressure or flow in afirst direction 46, e.g., normal venous blood flow, thereby opening apassageway 65 through theframe 11 and thelumen 34 of thevessel 33. As the muscles relax, producing flow in a second,opposite direction 47, e.g.,retrograde blood flow 47, as shown inFIG. 14 , thepartial covering 58 acts as a normal valve by catching the backward flowing blood and closing thelumen 34 of the vessel. In the case of theartificial valve 43, thepartial covering 58 is forced against the vessel wall to seal off thepassageway 65, unlike a normal venous valve which has two leaflets, which are forced together during retrograde flow. Both theartificial valve 43 of the illustrative embodiment and the normal venous valve, have a curved structure or cusp that facilitates the capture of the blood and subsequent closure. In addition to the triangular covering, other possible configurations of thepartial covering 58 that result in the cupping or trapping of fluid in one direction can be used. - Selecting the correct size of valve for the vessel ensures that the
partial covering 58 properly seals against thevessel wall 70. If thelumen 34 of the vessel is too large for thedevice 10, there will be retrograde leakage around thepartial covering 58. -
FIG. 15 depicts a top view of a fifth embodiment of the present invention in thefirst configuration 35, whereby there is afull covering 57 that generally covers theentire aperture 56 of theframe 11. When thedevice 10 is formed into thesecond configuration 36, as depicted inFIG. 16 , it becomes useful as anocclusion device 51 to occlude a duct or vessel, close a shunt, repair a defect, or other application where complete or substantially complete prevention of flow is desired. As an intravascular device, studies in swine have shown occlusion to occur almost immediately when deployed in an artery or the aorta with autopsy specimens showing that thrombus and fibrin which had filled the space around the device. The design of the present invention permits it to be used successfully in large vessels such as the aorta. Generally, the occlusion device should haveside 13 lengths that are at least around 50% or larger than the vessel diameter in which they are to be implanted. -
FIGS. 17-18 depict two embodiments of the present invention in which thedevice 10 functions as astent graft 75 to repair a damaged or diseased vessel, such as due to formation of an aneurysm.FIG. 17 shows astent graft 75 having atubular graft prosthesis 54 that is held in place by a pair offrames 11 that function asstent adaptors stent adaptor central opening 55 through which thegraft prosthesis 54 is placed and held in place by friction or attachment to prevent migration. One method of preventing migration is placement of astent adaptor graft prosthesis 54 to the covering of thestent adaptors barb 39 connects to eachstent adaptor stent graft 75. In the embodiment depicted inFIG. 18 , the covering 45 comprises aouter sleeve 64 that is held in place by first and second 30,31 frames that function asstents 44 to hold and seal thesleeve 64 against a vessel wall and maintain anopen passageway 65. In the illustrative embodiment, thestents 44 are secured to thegraft sleeve 64 bysutures 50 that are optionally anchored to thecoils 14 of thebends 12. If the embodiment ofFIG. 18 is used in smaller vessels, asingle frame 11 can be used at each end of thestent graft 75. Anotherstent graft 75 embodiment is depicted inFIG. 32 for repairing avessel defect 97, such as an aneurysm in a bifurcated vessel. Thestent adaptor 52 of the present invention is placed in thecommon vessel 96 such as the abdominal aorta. Twotubular grafts 54 are secured within anaperture 55 in the covering 45 of theframe 11 by one or moreinternal stent adapters 102, or another type of self-expanding stent, that bias the opening of thegrafts 54 against the surrounding covering 45 to provide an adequate seal. Eachleg stent graft prosthesis 75 transverses thevessel defect 97 and feeds into theirrespective vessel branches FIG. 17 , asecond stent adapter 53 can be used to anchor the other end of thetubular graft 54 in eachvessel branch -
FIGS. 20-27 and 35-41 depict embodiments of present inventions in which thedevice 10 comprises an implantable valve havingmultiple leaflets 25 that act together to regulate and augment the flow of fluid through a duct orvessel 33, or within the heart to treat patients with damaged or diseased heart valves. The covering 45 of each of these embodiments includes one or a series ofpartial coverings 58 that form theleaflets 25 of the valve. As with the other embodiments, the covering 45 may comprise a biomaterial or a synthetic material. While DACRON, expanded polytetrafluoroethylene (ePTFE), or other synthetic biocompatible materials can be used to fabricate the covering 45, a naturally occurring biomaterial, such as collagen, is highly desirable, particularly a specially derived collagen material known as an extracellular matrix (ECM), such as small intestinal submucosa (SIS). Besides SIS, examples of ECM=s include pericardium, stomach submucosa, liver basement membrane, urinary bladder submucosa, tissue mucosa, and dura mater. SIS is particularly useful, and can be made in the fashion described in Badylak et al., U.S. Pat. No. 4,902,508; Intestinal Collagen Layer described in U.S. Pat. No. 5,733,337 to Carr and in 17 Nature Biotechnology 1083 (November 1999); Cook et al., WIPO Publication WO 98/22158, dated 28 May 1998, which is the published application of PCT/US97/14855. Irrespective of the origin of the valve material (synthetic versus naturally occurring), the valve material can be made thicker by making multilaminate constructs, for example SIS constructs as described in U.S. Pat. Nos. 5,968,096; 5,955,110; 5,885,619; and 5,711,969. Animal data show that the SIS used in venous valves of the present invention can be replaced by native tissue in as little as a month=s time. In addition to xenogenic biomaterials, such as SIS, autologous tissue can be harvested as well, for use in forming the leaflets of the valve. Additionally Elastin or Elastin Like Polypetides (ELPs) and the like offer potential as a material to fabricate the covering or frame to form a device with exceptional biocompatibility. Another alternative would be to used allographs such as harvested native valve tissue. Such tissue is commercially available in a cryopreserved state. - To more completely discuss and understand the
multi-leaflet valve 43 embodiments of FIGS. 20-27,35-41, it is useful to now add certain supplemental terminology which in some instances, could be applied to the embodiments depicted in the earlier figures. In the illustrative multi-leaflet embodiments, thevalve 43 is divided into a plurality oflegs 113, each of which further comprises aleaflet 25. To anchor, support, and provide the proper orientation of theleaflets 25, a separate orintegral frame 11 is included, such as thewire frame 11 depicted inFIG. 1 . Ideally, the wire used to construct the frame is made of a resilient material such as 302,304 stainless steel; however, a wide variety of other metals, polymers, or other materials are possible. It is possible for the frame to be made of the same material as theleaflets 25. One other example of a suitable frame material would be a superelastic alloy such as nitinol (NiTi). Resiliency of theframe 11, which provides radial expandability to thevalve 43 when in thesecond configuration 36 for deployment, is not necessarily an essential property of the frame. For example,optional barbs 16 can provide the means to anchor thevalve 43 after delivery, even if thevalve 43 lacks sufficient expansile force to anchor itself against the vessel wall. Additionally, the frame can comprise a ductile material with thedevice 10 being designed to be balloon expandable within the vessel. - Typically, when used as a valve to correct venous insufficiency in the lower extremities, the
valve 43 in situ comprises a plurality ofbends 12 of the frame, that provide the majority of the outward radial force that helps anchor the device tovessel wall 70, as depicted inFIGS. 22-27 . When deployed, the frame assumes the undulating or serpentine configuration characteristic of the invention with a first series ofbends 115 of the first or proximal end alternating with a second series ofbends 116 of the second or distal end, with the second ordistal bends 116 being located at the bottom of the valve distal to the heart and the first orproximal bends 115 being located at the top of the valve proximal to the heart. It should be understood that the valve can assume other orientations, depending on the particular clinical use, and thus, any directional labels used herein (>distal=, >top=, etc.) are merely for reference purposes. Theleaflet 25, which generally covers thevalve leg 113 and therefore, assumes the same roughly triangular >U=or >V=shape of that portion of theframe 11 perimeter, includes an resilient arcuateouter edge 112 that conforms to and/or seals with the contours of thevessel wall 70, and aninner edge 11 that traverses thevessel lumen 34. The central portion orbody 156 of theleaflet 25 extends inward from thevessel wall 70 andouter edge 112 in an oblique direction toward thefirst end 68 of thevalve 43 where it terminates at the inner edge 111 thereof. The valve leaflets that come in contact with the vessel wall can also be arcuate as the supporting frame to better conform to and seal wit the vessel wall. Theleaflets 25 assume a curvilinear shape when in the deployedconfiguration 36. The portion of thebody 156 proximate the inner edge 111 is sufficiently flexible such that is can move in and out of contact with the inner edge 111 the opposite orother leaflets 25; however, the remainder of thebody 156, particular that near theouter edge 112 orsecond end 69 of thedevice 10, can be made less flexible or even rigid in some instances, essentially functioning more for support, similar to the function of theframe 11, rather than to cooperate with other leaflet(s) 25.FIGS. 20-27 depict the present invention as an implantable, intraluminal, vascular adapted for use as aimplantable multi-leaflet valve 43 including astent 44 orframe 11 with at least apartial covering 58. The covering comprises a first and asecond valve leaflets aperture 56 within theframe 11 while thevalve 43 is in the deployedconfiguration 36 and forms theopening 117 or valve orifice which regulates the flow offluid FIG. 20 shows thedevice 10 in the first, generallyplanar configuration 35 where theframe 11 is generally rectangular or in particular square in shape. Thepartial covering 58 forming theleaflets entire frame 11 with theaperture 56 comprising aslit 108 that extends across thefirst axis 94 of theframe 11, the first axis being defined as traversing diagonally opposite bends (22 and 23 in this example) that are in line with thevalve orifice 117 that forms thevalve 43. The covering 45 is therefore divided into at least first and second portions (making it a partial covering 58) which define the first andsecond valve leaflets leaflets complete covering 45 can be slit open along the axis after it is affixed to the frame, or at least first and second adjacent triangular portions (partial coverings 58) can be separately attached, eliminating the need for mechanically forming aslit 108. In the embodiment ofFIG. 20 , theslit 108 is made in the covering 45 such that the slit terminates a few millimeters from each of the corner bends 22,23, creating a pair ofcorner gaps 155, thereby eliminating two of the most likely sources of leakage around thevalve 43. In the illustrative embodiments, theouter edge 112 of thepartial covering 58 that comprises theleaflet 25 is stretched over theframe 11 comprising thevalve leg 113 and sutured or otherwise attached as disclosed herein. Theleaflet 25 is secured in place such that the material is fairly taut, such that when thevalve 43 is situated in thevessel 33 and its diameter constrained to slightly less than thevalve width 146, theleaflet 25 assumes a relatively loose configuration that gives it the ability to flex and invert its shape, depending on the direction of fluid flow. The inner edge 111 of theleaflet 25 is generally free and unattached to the frame and generally extends between thebends 22 and 23 (thebends 115 of the first end) of thevalve leg 113. The inner edge 111 may be reinforced by some means, such as additional material or thin wire, that still would allow it to be sufficiently pliable to be able to seal against anotherleaflet 25 whenretrograde flow 47 forces theleaflets leaflet 25 is sized and shaped such that the inner edge 111 of oneleaflet 78 can meet or overlap with the inner edge 111 of the opposing leaflet 79 (or leaflets, e.g., 119,120), except when degree of normal,positive flow 46 is sufficient to force theleaflets 25 open to permit fluid passage therethrough. - The embodiments of
FIGS. 21-27 are configured into anelongated diamond shape 153 in theplanar configuration 35 with the distance between the two bends 22,23 aligned with thevalve orifice 117 andfirst axis 94 being less than the distance betweenbends perpendicular axis 95. Thisdiamond configuration 153 can be accomplished by forming theframe 11 into that particular shape, or constraining a square frame into adiamond shape 153, which will be discussed later. By configuring thevalve 43 into thediamond shape 153, thevalve legs device 10 during deployment, provides more surface area to receive retrograde flow, and more closely mimics a natural venous valve. In the deployedconfiguration 36 of the embodiment ofFIG. 21 , which is shown inFIGS. 22-25 , thevalve leaflets FIGS. 22,24 ). Therespective valve leaflets Retrograde blood flow 47 forces thevalve leaflets FIGS. 23 and 25 thereby closing off thelumen 34 of thevessel 33 and thevalve orifice 117. -
FIGS. 21A-21B depict embodiments of thevalve 43 in which eachleaflet flap 77 of overhanging material along the slit edge 111 to provide advantageous sealing dynamics when thevalve 43 is in the deployedconfiguration 36 as depicted inFIGS. 22-25 . Theflaps 77 are typically formed by suturing two separate pieces of covering 45 material to the frame such that the inner edge 111 is extendable over theslit 108 and inner edge 111 of theadjacent leaflet 25. By overlapping with anadjacent flap 77 orleaflet 25, theflap 77 can provide additional means to help seal thevalve orifice 117. Two embodiments ofleaflets 25 withflaps 77 are shown. InFIG. 21A , the inner edge 111 is basically straight and extends over thefirst axis 94 of theframe 11. Theflaps 77 can be cut to create acorner gap 155 that covers and seals the corner region around thebend FIG. 21B , theflap 77 is cut such that there is anotch 157 in the leaflet where the leaflet meets the corner bends 22,23. While theseflaps 77 may provide benefit in certain embodiments, theoptional flaps 77 shown inFIG. 21 are not necessary to provide a good seal againstbackflow 47 if thevalve 43 andleaflets 25 are properly sized and configured. -
FIGS. 26-26A depict one method of affixing a covering 45 comprising a biomaterial, such as SIS, to theframe 11 which has been constrained using a temporary constrainingmechansim 121, such as a suture, to acheive the desired frame configuration. As shown inFIG. 26 , the covering 45 is cut larger than theframe 11 such that there is anoverhang 80 of material therearound, e.g, 5-10 mm. Theframe 11 is centered over the covering 45 and theoverhang 80 is then folded over from onelong side 142, with the otherlong side 143 subsequently being folded over the first. As shown inFIG. 26A , the covering 45 is sutured to the frame along oneside 142, typically usingforceps 158 and needle, thereby enclosing theframe 11 and the coiledeyelet 14 with theoverhang 80 alongside 142. The covering 45 is sutured to the frame with resorbable ornon-resorbable sutures 50 or some other suitable method of attaching two layers of biomaterials can be used. In the case of SIS, a single ply sheet, usually about 0.1 mm thick, is used in the hydrated condition. In the illustrative embodiments, 7-0 Prolene suture is used, forming a knot at one bend (e.g., bend 20), then continuing to the next bend (e.g., 22) with a runningsuture 50, penetrating the layers of SIS around the frame at about 1-2 mm intervals with loops formed to hold thesuture 50 in place. When thenext coil turn 14 is reached, several knots are formed therethrough, and the runningsuture 50 continues to thenext coil turn 14. If barbs are present, such as shown in the embodiment ofFIG. 21 , thesuture 50 is kept inside of thebarbs 16 located about eachcoil turn 14. In the illustrative example, the covering 45 is affixed to theframe 11 such that one side of theoverhang 80 is not sutured over the other side in order to maintain the free edge of theoverhang 80, although the alternative condition would be an acceptable embodiment. Alternative attachment methods include, but are not limited to, use of a biological adhesive, a cross-linking agent, heat welding, crimping, and pressure welding. For synthetic coverings, other similar methods of joining or attaching materials are available which are known in the medical arts. The covering 45, whether made from a biomaterial or synthetic material, can be altered in ways that improve its function, for example, by applying a coating of pharmacologically active materials such as heparin or cytokines, providing a thin external cellular layer, e.g., endothelial cells, or adding a hydrophilic material or other treatment to change the surface properties. - Once the covering 45 has been sutured into place or otherwise attached to the frame, the
overhang 80 is folded back away from the frame, as shown on thesecond side 143 of the frame ofFIG. 26A , and part of theexcess overhang 80 is trimmed away with ascalpel 159 or other cutting instrument to leave a 2-4 mm skirt around theframe 11. Theoverhang 80 or skirt provides a free edge of SIS (or material with similar remodeling properties) to help encourage more rapid cell ingrowth from the vessel wall, such that the SIS replaces native tissue as quickly as possible. An unattached edge of theoverhang 80 can also form acorner flap 81 or pocket as depicted inFIG. 27 . Thiscorner flap 81 can serve to catchretrograde blood flow 47 to provide a better seal between thedevice 10 and thevessel wall 70 as well as providing an improved substrate for ingrowth of native intimal tissue from thevessel 33, if made of SIS or another material with remodeling properties. - Referring now to
FIGS. 28-31 , theframe 11 used to form thevalve 43 embodiments, e.g.,FIGS. 20-27 , that are placed in the legs or other deep veins as replacement for incompetent venous valves, is sized according to the size of the target vessel. For example, a typical venous valve might be made of 0.0075″ 304 stainless steel mandril wire with anattachment mechanism 15 comprising 23 to 24 gauge thin-wall stainless steel cannula or other tubing. Larger wire (e.g., 0.01″) andattachment cannula 15 are typically used forvalves 43 of the larger diameter (greater than 15 mm). Selection of theattachment cannula 15 depends on competing factors. For example, use of largergauge attachment cannula 15 results in a slightly increaseddevice 10 profile, yet it includes additional room for flux when theattachment mechanism 15 is soldered over thecontinuous wire 59 comprising theframe 11.FIG. 30 best depicts an uncoveredframe 11 used to form avenous valve 43, wherein the length of thesides 13 typically range from about 15 to 25 mm. For larger frames, heavier gauge wire is typically used. For example, 25 mm frames might use 0.01″ wire, with larger diameter embodiments such as stent occluders used for femoral bypass or stent adaptors, such as shown inFIGS. 17 and 32 , requiring an even heavier gauge. The appropriate gauge or thickness of the frame wire also depends on the type of alloy or material used. As previously disclosed, the frame is typically formed in a generally flat configuration and then manipulated into its characteristic serpentine configuration and loaded into a delivery system. Therefore, the frame usually will tend to reassume the first or generally flat configuration if the restraint of the delivery system or vessel is removed. Deformation of theframe 11 can occur after it has been manipulated into the second configuration, however, such that it no longer will lie completely flat, as depicted inFIG. 34 . This angle ofdeformation 129, which varies depending on the frame thickness and material used, generally does not compromise the function of thedevice 10, which can be reconfigured into the serpentine configuration (of the second, deployed configurations) without loss of function. - The
frame 11 of the present invention can be made either by forming a series of bends in a length of straight wire and attaching the wire to itself, as previously discussed, to form a closed configuration, or theframe 11 can be formed in the deployment (second)configuration 35 as depicted inFIGS. 41-41A by cutting it out of aflat sheet 152 of material, e.g., stainless steel or nitinol. Further finishing procedures can then be performed after it has been cut or formed, such as polishing, eliminating sharp edges, adding surface treatments or coatings, etc. In addition to metal, theframe 11 can comprise one or more polymers, composite materials, or other non-metallic materials such as collagen with the frame either being cut from a thin sheet of the material, or molded into thedeployment configuration 36 as depicted inFIG. 43 . Unlike the majority of the depicted embodiments, theframe 11 ofFIG. 43 does not naturally assume a flattenedconfiguration 35 when thedevice 10 is unconstrained by the vessel or delivery system. - The illustrative embodiments of
FIGS. 41-41A and 43 includeintegral barbs 124 that extend from theframe 11, which being formed as a closed frame, does not have free ends 60,61 that can be used to serve asbarbs 16 as depicted inFIG. 3 and other embodiments.FIGS. 41-41A depict a series ofintegral barbs 124 comprising V-shapedcuts 139 transversing the thickness of theflat metal frame 11, which are bent outward to form thebarb 16. In the embodiment ofFIG. 43 , theintegral barbs 124 are formed along with theframe 11 with two extending from the frame at either side of eachbend 12. Theseintegral barbs 124 can be designed into the mold if theframe 11 is formed out of a polymer material. The number, arrangement, and configuration of theintegral barbs 124 is generally not critical and can vary according to design preference and the clinical use of the device. Thebarbs 16 may or may not penetrate the covering, depending on their design and other factors, including the thickness and type of covering used. - While the frame embodiment of
FIG. 43 can be formed from a variety of medical grade polymers having properties that permit the frame to function as a supporting structure for thevalve leaflets frame 11 from a material that can be degraded and adsorbed by the body over time to advantageously eliminate a frame structure can would remain in the vessel as a foreign body and that could possibly fracture and/or cause perforation of the vessel wall. A number of bioabsorbable homopolymers, copolymers, or blends of bioabsorbable polymers are known in the medical arts. These include, but are not necessarily limited to, poly-alpha hydroxy acids such as polyactic acid, polylactide, polyglycolic acid, or polyglycolide; trimethlyene carbonate; polycaprolactone; poly-beta hydroxy acids such as polyhydroxybutyrate or polyhydroxyvalerate; or other polymers such as polyphosphazines, polyorganophosphazines, polyanhydrides, polyesteramides, polyorthoesters, polyethylene oxide, polyester-ethers (e.g., polydioxanone) or polyamino acids (e.g., poly-L-glutamic acid or poly-L-lysine). There are also a number of naturally derived bioabsorbable polymers that may be suitable, including modified polysaccharides such as cellulose, chitin, and dextran or modified proteins such as fibrin and casein. -
FIGS. 44-46 depicts two exemplary embodiments in which theframe 11 is integral with the covering 45. In the embodiment ofFIG. 44 , thevalve 43 is formed as a single piece of material, such as a flexible polymeric or collagen-based material, whereby there is a thin, compliant central portion comprising the covering 45 orleaflets edge 141 portion that comprises theframe 11. Thevalve 43, shown in the generallyflat configuration 35, can be also formed into the deployment configuration 36 (seeFIG. 43 ). Optionally, the material of theframe 11 portion can be subjected to treatments or processes that add rigidity or other desired characteristics that permit the frame to better support the covering 45 portion or anchor thedevice 10 to the vessel wall. As with the embodiment ofFIG. 43 , optionalintergral barbs 124 can be included along theframe 11. In addition to forming a thickenededge 141 to serve as theframe 11, other layers of different materials can be laminated to or blended with the edge portion to provide the desired properties. As another alternative to the thickenededge 141 portion ofFIGS. 44-45 , theoutside edge 112 of the covering 45 can be folded over itself to form a rolled edge 140 (FIG. 46 ) that adds rigidity to serve as aframe 11. Therolled edge 140 can be held in placed with a glue, resin, orsimilar bonding agent 144. For example, the covering 45 and rollededge 140 can comprise a sheet of SIS with abonding agent 144 such as collagen glue or other bioabsorbable material used to secure the rolled portion and after hardening, to add the necessary degree of rigidity for the valve 43 (or occluder, filter, stent adaptor, etc.) to assume the deployment configuration within the vessel. Excess of thebonding agent 144 can be fashioned to structural elements that can serve to help anchor thedevice 10 within the vessel. It is also within the scope of the invention to eliminate adiscernable frame 11 by changing the material or material properties along theouter edge 112 of the leaflets, by adding or incorporating one or more different material or agents along theouter edge 112 of covering 45 such that the stiffness and/or resiliency increased, thereby allowing the frame to hold a desired shape during deployment, while still allowing the adjacent covering material to be sufficiently flexible to function as aleaflet 25. If theillustrative valve 43 lacks the radial expandability to anchor itself to the vessel wall, it may be mounted on a balloon to expand thevalve 43 and anchor the barbs, if present, into the vessel wall. - The illustrative embodiments of the present invention generally include a
closed frame 11 to give thedevice 10 its form.FIG. 47 depicts an example in which theframe 11 portion is not a closed structure. Rather, a portion of the covering 45 used to span agap 145 in the frame such that a portion of the outside edge 112 (ofleaflet 79 in this example) is unsupported therealong. The length of thegaps 145 and their distribution can vary as long as theframe 11 is still able to fulfill its role to support and define the shape of thevalve 43 ordevice 10. -
FIGS. 21-31 depict various embodiments in which thebends more bends 12 of thedevice frame 11 can alter the properties of theframe 11 and result in improved sealing characteristics or the ability of thedevice 10 to impinge upon thevessel wall 70 to prevent migration or shifting. In the illustrative embodiments, thecoil turn 14 is formed as previously disclosed whereby eachbend 12 is in a untensioned state with theadjacent sides 13 having an initial angle after formation of thebend 12. For example, in the embodiment ofFIG. 20 , theinitial angle 109 after the bends are formed and thefinal angle 110 after theframe 11 is assembled are both approximately 90□. Therefore, thebends 12 of the embodiment ofFIG. 20 are not placed under any significant degree of tension. In the embodiments ofFIGS. 21-31 , the frame is restrained to permanently place thebends 12 under tension such that the angle between thesides bend 12 is increased or decreased by some method of manipulation to produce a resiliently tensioned bend 118 (FIGS. 26 and 29 ) having afinal angle 110 different than the initial angle 109 (e.g.,FIG. 28 ). - Referring particularly to
FIGS. 21-28 , the covering 45 (including a full or a partial covering 58) can be attached to theframe 11 of thevalve 43 or other embodiment of the present invention, to constrain a generally untensioned square frame 11 (such as inFIG. 1 ) and subsequently form an altered shape 82, such as adiamond 153, in which the distance betweenbends bends FIG. 21 as reference, theangle 110 measured between theadjacent sides 13 frombends corresponding angles 161 measured atbends frame 11 shape serves to add tension in each of the bends, which allows better positioning of thedevice 10 against thevessel wall 70 while in the deployed configuration, as shown inFIGS. 22-25 . Additionally, constraining theframe 11 along thefirst axis 94 of theslit 108 allows thatdistance 146 to be adjusted to provide the optimum size for thevessel 33 into which thevalve 43 is to be implanted. Assuming aresilient frame 11 is being used that makes thevalve 43 radially expandable, it would normally be preferential to slightly oversize thevalve 43 along at thewidth 146 of the frame 11 (along first axis 94) when thevalve 43 is in the generally flattenedconfiguration 35, thereby causing theleaflets valve 43 is in the deployedconfiguration 36 and being constrained slightly by thevessel 33. The proper length of the constrainedframe 11 as measured diagonally betweenbends leaflets blood flow 46 that most closely mimics that found in a normal functioning valve. - Dog studies by Karino and Motomiya (Thrombosis Research 36: 245-257) have demonstrated that there is about a 60 to 70% constriction of blood flow through the natural valve. In the
valve 43 of the present invention, theleaflets 25 should ideally span about 30-60% of thevessel 33 diameter across. If it is much less than 30%,blood flow 46 may be impeded to an unacceptable degree, while if theleaflets vessel wall 70 and therefore, not close properly in the presence ofretrograde flow 47. Theframe 11 can be formed or constrained such that thedistance 146 betweenpoints valve 43 is stretched tight across theframe 11 and is very limited in the amount of blood that will allow to pass through. To give the leaflets the flexibility and compliance to open to permit flow and then close to seal against backflow, theslit axis distance 146 of thevalve 43 should be oversized with respect to the diameter of the vessel into which it is to be placed. Constraining thevalve 43 along thefirst axis 94 such that it sized a few mm larger than the lower extreme (2 r) or a few mm larger than the upper extreme (πr), not only allows the leaflets to function in a more optimal manner, but also allows thevalve 43 to safely and effectively impinge on the vessel wall to seal and reduce the possibility of migration. The ideal amount of oversize is largely dependent on the size and diameter of theframe 11 prior to resizing.FIG. 49 depicts a schematic top view of the valve ofFIG. 22 showing thelength 147 of the orifice, thewidth 148 of the orifice, theportion 154 of the vessel occluded by aleaflet 25, and thecorner gaps 155 than exist between eachlateral edge 156 of thevalve orifice 117 and theouter edge 112 of the leaflet 25 (or the frame 11). The following formula can be to approximate the elliptic circumference (C) of thevalve orifice 117, where a=one half thelength 147 of the orifice, and b=one half thewidth 148 of the orifice 117: - Assuming that we wish to size the
valve 43 to produce anorifice 117 that opens approximately 30-60% of the vessel lumen 34 (with theoccluded portions 154 comprising 40-70% of the same), the preceding formula can be used to determine the amount of oversize that produces the desired characteristics. The amount of oversize (valve width 146 in the flat configuration minus the diameter of the vessel lumen 34) would generally range from 1-2 mm for smaller valves (those placed in 8-9 mm vessels) up to 3-4 mm for valves intended for larger vessels (17-21 mm). For example, a valve intended for a 14 mm vessel should ideally have a 2-3 mm oversize if the range of 30-60% opening is to be maintained. If theframe 11 of avalve 43 having 20 mm sides is constrained such that the distance betweenbends valve 43 opens approximately 43%, which is well within the most desired range. If constrained to 17 mm, thevalve 43 is able to open up to approximately 55% of the vessel diameter. In contrast, oversizing thevalve 43 by 6 mm, produces alarge orifice 117 of 83% which lies outside the target range, although it would certainly produce avalve 43 capable of opening and closing in response tofluid flow valve 43 in which the valve width in the generally flattenedconfiguration 35 is 17-18 mm, which would be avalve 43 sized to accommodate a 14-15 mm vessel, the 20mm frame 11 should be constrained such that the distance betweenbends FIG. 26 , theframe 11 is constrained across thefirst axis 94 using a temporary constrainingmechanism 121, such as by tying a suture through the coil turns 14 ofbends suture 121 is cut, which results in a slight expansion in the width of theframe 11 as the SIS stretches under the tension of the constrained frame, resulting in the desired final width of 17-18 mm. The amount of expansion varies with the compliance of theparticular covering 45 as well as the resiliency of theframe 11. Although the desiredfinal width 146 of the constrainedframe 11 can result from a relatively wide range ofinitial frame 11 sizes, depending on how much the frame is constrained, generally, larger sized frames (e.g., sides measuring about 25 mm) are most suitable for larger vessels (e.g., 16-21 mm in diameter), while smaller frames (e.g., 15 mm) are most suitable for smaller diameter vessels (e.g., 8-9 mm). While this range represents the most common sizes used for correcting venous valve insufficiency in the lower legs,valves 43 of the present invention can be made in a much larger range of sizes to treat veins or other vessels elsewhere in the body. -
FIGS. 28-31 depict another embodiment of the present invention in which aopen frame 11, such as depicted inFIG. 28 , is assembled into a square frame (FIGS. 29-31 ) such thebends 12 are put under tension. The resiliently tensionedbends 118 in the assembled device (as shown inFIGS. 29-31 ) result from theinitial angle 109 formed inwire frame 11 before being assembled into a closed circumference 62 (FIG. 28 ), being greater than thefinal angle 110. To form the embodiment ofFIG. 1 , for example, the wire is wrapped around a pin to form the coil turns 14 with thesides 13 generally lying about 90□ with respect to one another. Theattachment mechanism 15 then secures and closes theframe 11 to form the final square shape. In the embodiments ofFIGS. 28-31 , thefirst angle 109 is made approximately 150□, rather than 90═, which is the desiredfinal angle 110. While the wire is not under stress after thebends 12 are initially formed, thebends 12 andsides 13 are stressed when thedevice 10 is constrained during assembly to form the four-sided, generally square shape. In particular reference toFIG. 30 , thesides bend 118 becomes somewhat deformed when thebend 12 is put under stress, generally assuming a bowed shape between the adjacent bends. By creating this >rounded square=with tensioned or stressedbends 118, thesides 13 of theframe 11 are able to better conform to the roundedvessel wall 70 than would aside 13 that is initially straight prior to deployment. Additionally, by rounding thedistal bends 116 of thevalve legs 113, it may also reduce the potential for thevalve legs 113 to cause trauma to thevessel 33 as they continue to exert force thereupon. - An additional method of constraining the
valve 43, or similar type device 10 (e.g., occluder, filter, stent, stent adaptor), is depicted inFIG. 48 in which a circumferentially constrainingmechanism 125, is added to at least partially encircle theframe 11 while it is in both the delivery configuration 37 (FIG. 6 ) and the deployedconfiguration 36 such that thedevice 10 is limited in its ability to radially expand. Once the device reaches its maximal radial expansion, the outward force thedevice 10 places on thevessel wall 70 is eliminated, thereby reducing potential damage thereto (e.g., from an improperly sized valve), such as tissue erosion possibly resulting in eventual perforation of thevessel 33. In the illustrative embodiment, thecircumferentially constraining mechanism 125 comprises a suture that is affixed to and completely encircles theframe 11 to limit the outward expansion of thevalve legs sides 13 of thevalve legs FIG. 39 fulfilling a different function, that provides an effective attachment point through which to feed and/or affix thesuture restraint 125. In the illustrative embodiment, thesuture restraint 125 is in a relaxed state when thedevice 10 is loaded in the delivery system. Then, as thedevice 10 is deployed, it expands within thevessel 33 until it is constrained by thesuture restraint 125 if thedevice 10 has been properly sized such thatvessel 33 does not provide constraining forces sufficient to prevent thedevice 10 from fully expanding to its predetermined maximum diameter. If the device is undersized for the diameter of the vessel, it may be subject to migration due to insufficient expansion. The illustrative embodiment is merely exemplary of the numerous available circumferentially constrainingmechanisms 125. It is not necessary that thecircumferentially constraining mechanism 125 completely encircle thedevice 10. For example, short pieces of suture or another type of tethering mechanism, such as a section of webbing or other material, can be affixed between the sides of the valve legs to limit their expansion, or the frame can include an integral circumferentially constraining mechanism, such as an expandable strut formed as part of the frame. The strut would unfold as the frame radially expands and limits how far the sides of the valve leg to which is attached, can spread apart relative to each other, thereby limiting the outward radial force from the device against the vessel wall. - Another possibility is for circumferentially constraining
mechanism 125 to comprise asleeve 162 of flexible material, such as SIS around thevalve 43, as depicted inFIG. 50 , which is of a diameter appropriate for deployment within the target vessel 33 (typically, being slightly larger than the target vessel diameter) that allows the valve to anchor thereto. Thesleeve 162 could be affixed to theframe 11 withsutures 50 or by some other means as thevalve 43 is held in a collapsed condition prior to loading thedevice 10, including thesleeve 162, into a delivery system. Thesleeve 162 enclosed the length of thevalve 43, or thebends 12 andbarbs 16 can be left uncovered, as shown. To reduce resiliency of thesleeve 162, tethers and other types of circumferentially constrainingmechanism 125 can be used in combination with thesleeve 162 to limit radial expandability of thevalve 43. It should be noted that if thecircumferentially constraining mechanism 125 itself is a resilient member, it will only serve to reduce the outward force of thedevice 10 against thevessel wall 70 until maximum expansion is reached. -
FIGS. 30-31 depict alternative methods of forming theframe 11 and attaching barbs thereto. In the embodiment shown inFIG. 30 ,attachment mechanisms FIG. 29 . Rather than placing theattachment mechanisms 15 at thepoint 87 where the respective ends 60,61 of thewire frame 11 cross to form the square shape, twoattachment mechanisms cross point 87. Having anadditional attachment mechanism side 13 provides better fixation of the frame with little additional metal and helps prevent twisting of theframe 11. On the opposite side which contains the double endedbarb 39, thedouble attachment mechanisms FIG. 31 , threeattachment mechanisms frame 11 as well as serving as attachment points for includingsupplemental barbs device 10 to thevessel wall 70. Theillustrative barbs 16 are typically configured such that they extend only a short distance (less than 1-2 mm) beyond thebends 12; however, thebarbs 16 can be made virtually any practical length, such as extending them more than 1 cm beyond thebends 12 to aid in stabilizing thedevice 10 upon deployment such that it does not shift laterally and end up being cockeyed within the vessel. To assist in this function, the barbs can be shaped accordingly, rather than be limited to a substantially straight configuration. - The present invention is not limited to a two-leaflet valve 43 (or two-leg occluder or stent adaptor, etc.).
FIGS. 35-40 depictmulti-leaflet valves 43 having three or fourvalve legs 113 andleaflets 25. The addition of additional leaflets reduces the load produced by the fluid column upon eachindividual leaflet 25. This in turn, puts less stress upon the sutures or attachment points of the covering 45, thereby allowing thevalve 43 to function under higher pressures than would otherwise be possible. For example, thesevalves 43 could prove advantageous for use on the arterial side, such as to augment pulmonary valves, or within the heart itself, where pressures exerted on the leaflets can be significantly higher than normally found on the venous side.FIG. 35 depicts avalve 43 which in the generally flattenedconfiguration 35, has a threelegs valve orifice 117. When theillustrative valve 43 is placed in thevessel 33 for which it has been properly sized, as depicted inFIG. 37 , theleaflets additional legs 113 to distribute the load over a larger number of attachment points 50 (e.g., sutures) and add positional stability to thedevice 10, can be applied to occluders and stent adaptors as well. - One method of forming the embodiment of
FIG. 35 , involves constructing a triangular-shapedframe 1, as shown inFIG. 36 , that includes an intermediatecoiled eyelet 132 formed at the midpoint of each of the threesides 13. A temporary constrainingsuture 121, such as that shown inFIG. 38 , is threaded through each of theintermediate eyelets 132, drawing them inward to form threeadditional bends legs FIG. 35 ), depending how tightly the constrainingsuture 121 is drawn. At this point, the covering 45 is attached to theframe 11, either as threeseparate leaflets valve orifice 117 is formed. After the covering 45 has been secured to theframe 11, the constrainingsuture 121 is cut and removed. As depicted, thebarbs 16 are affixed to the triangular shaped frame ofFIG. 36 , two per side, such that they terminate on either side ofintermediate eyelet 132. Thus, when theintermediate eyelets 132 are drawn inward to create sixsides 13, each includes abarb 16. - The embodiment of
FIGS. 38-40 , which includes fourlegs FIGS. 35-37 . Theframe 11 is initially formed in a square configuration (FIG. 39 ) with intermediately placedcoiled eyelets 132 at the midpoint of eachside 13, dividing the side into a first andsecond side portion FIG. 38 , the temporary constrainingsuture 121 is used to draw the eyelets inward where they form the fouradditional bends valve legs second sides portions sides 13 ofadjacent valve legs valve orifice 117 is created when the fourleaflets legs frame 11. One should appreciate that valves with more than four legs would be made in a similar manner to the embodiments above with a five-sided valve being formed from a pentagon, a six-sided valve being formed from a hexagon, etc. - Delivery of the
device 10 of the present invention can be accomplished in a variety of ways. One method, depicted inFIG. 33 , involves the use of adelivery system 103 similar to that used to deliver embolization coils. Thedelivery system 103 comprises anouter member 105, such as a cannula or catheter, and an coaxialinner member 105 that includes atethering tip 107, such as a notched cannula, adapted to receive abarb 17 extending from theframe 11. Thetip 104 of the barb is configured such that it can positively engage with thetethering tip 107. This can be accomplished by adding a projection, such as a secondary barb, hook, spine, etc. to thetip 104, or otherwise enlarging the diameter thereof such that it can be releasably secured by thetethering tip 107 until deployment. The coaxialinner member 106 also includes anouter sheath 149 that retains and the locks thebarb tip 104 within thetethering tip 107 until it is advanced or retracted by manipulation of a proximal handle (not shown) to expose thenotch 150 in the tethering tip, which releases thebarb 17 and deploys thedevice 10. Thedevice 10 is preloaded within theouter member 105. The coaxialinner member 106 and attacheddevice 10 are then advanced together from theouter member 106 at the target site. Further manipulation of the proximal handle, advances thetethering tip 107, which in this particular embodiment, includes acoiled spring 151, relative to theouter sheath 149. After thedevice 10 has been released from thetethering tip 107, the spring-activated handle is released and theouter sheath 149 slides back over thetethering tip 107. The coaxialinner member 106 is withdrawn into theouter member 105 and theentire delivery system 103 is removed from the patient. As shown inFIG. 33 , thebarb tip 104 extends just beyond thecoil turn 14 of theframe 11 so as to have sufficient room to engage with the coaxialinner member 106. Thebarb tip 104 must be positioned to account for whether thedevice 10 is to be placed using a femoral approach or a superior approach. - The
illustrative delivery system 103 represents only one of many possibilities. For example, thedevice 10 can be attached to a delivery device using screws, clips, magnets, or some other tethering mechanism, or can be deployed by applying electrical current, heat, or some other means to cause detachment with a carrying mechanism. As previously disclosed, rather than making thedevice 10 self-expanding, where it is pushed from some sort tubular device, it can be formed from a ductile material, mounted over a balloon or other inflatable or expandable delivery mechanism, and deployed by expanding the device in that manner. - It is thus seen that the present invention includes devices having a number of configurations with regard to the frame, covering, barbs, etc. Futhermore, it has been seen that the invention and can be formed in a variety of ways using a different types of medical grade materials, and has utility to treat a wide range of medical problems. The embodiments contained herein should be considered merely exemplary as one skilled in the medical arts would appreciate that further modifications would be possible that would be included within the spirit of the invention.
Claims (42)
Priority Applications (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US10/910,490 US20050143807A1 (en) | 2000-02-03 | 2004-08-03 | Implantable vascular device comprising a bioabsorbable frame |
Applications Claiming Priority (3)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US18000200P | 2000-02-03 | 2000-02-03 | |
US09/777,091 US7452371B2 (en) | 1999-06-02 | 2001-02-05 | Implantable vascular device |
US10/910,490 US20050143807A1 (en) | 2000-02-03 | 2004-08-03 | Implantable vascular device comprising a bioabsorbable frame |
Related Parent Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US09/777,091 Continuation US7452371B2 (en) | 1998-06-02 | 2001-02-05 | Implantable vascular device |
Publications (1)
Publication Number | Publication Date |
---|---|
US20050143807A1 true US20050143807A1 (en) | 2005-06-30 |
Family
ID=26875897
Family Applications (6)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US09/777,091 Expired - Lifetime US7452371B2 (en) | 1998-06-02 | 2001-02-05 | Implantable vascular device |
US10/721,582 Expired - Lifetime US7597710B2 (en) | 1998-06-02 | 2003-11-25 | Implantable vascular device |
US10/910,490 Abandoned US20050143807A1 (en) | 2000-02-03 | 2004-08-03 | Implantable vascular device comprising a bioabsorbable frame |
US11/165,600 Expired - Lifetime US7520894B2 (en) | 1998-06-02 | 2005-06-22 | Implantable vascular device |
US12/258,757 Expired - Fee Related US8613763B2 (en) | 1998-06-02 | 2008-10-27 | Implantable vascular device |
US12/393,819 Expired - Lifetime US8444687B2 (en) | 1998-06-02 | 2009-02-26 | Implantable vascular device |
Family Applications Before (2)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US09/777,091 Expired - Lifetime US7452371B2 (en) | 1998-06-02 | 2001-02-05 | Implantable vascular device |
US10/721,582 Expired - Lifetime US7597710B2 (en) | 1998-06-02 | 2003-11-25 | Implantable vascular device |
Family Applications After (3)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US11/165,600 Expired - Lifetime US7520894B2 (en) | 1998-06-02 | 2005-06-22 | Implantable vascular device |
US12/258,757 Expired - Fee Related US8613763B2 (en) | 1998-06-02 | 2008-10-27 | Implantable vascular device |
US12/393,819 Expired - Lifetime US8444687B2 (en) | 1998-06-02 | 2009-02-26 | Implantable vascular device |
Country Status (1)
Country | Link |
---|---|
US (6) | US7452371B2 (en) |
Cited By (177)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20050075729A1 (en) * | 2003-10-06 | 2005-04-07 | Nguyen Tuoc Tan | Minimally invasive valve replacement system |
US20050261669A1 (en) * | 1998-04-30 | 2005-11-24 | Medtronic, Inc. | Intracardiovascular access (ICVA™) system |
US20060004442A1 (en) * | 2004-06-30 | 2006-01-05 | Benjamin Spenser | Paravalvular leak detection, sealing, and prevention |
US20060089708A1 (en) * | 2002-02-20 | 2006-04-27 | Osse Francisco J | Venous bi-valve |
US20060235512A1 (en) * | 2005-03-31 | 2006-10-19 | Cook Incorporated | Valve device with inflatable chamber |
US20070027528A1 (en) * | 2005-07-29 | 2007-02-01 | Cook Incorporated | Elliptical implantable device |
US20070027460A1 (en) * | 2005-07-27 | 2007-02-01 | Cook Incorporated | Implantable remodelable materials comprising magnetic material |
US20070027535A1 (en) * | 2005-07-28 | 2007-02-01 | Cook Incorporated | Implantable thromboresistant valve |
US20070061002A1 (en) * | 2005-09-01 | 2007-03-15 | Cook Incorporated | Attachment of material to an implantable frame by cross-linking |
US20070162103A1 (en) * | 2001-02-05 | 2007-07-12 | Cook Incorporated | Implantable device with remodelable material and covering material |
US20070191922A1 (en) * | 2006-01-18 | 2007-08-16 | William A. Cook Australia Pty. Ltd. | Self expanding stent |
US20080046071A1 (en) * | 2006-08-21 | 2008-02-21 | Dusan Pavcnik | Biomedical valve devices, support frames for use in such devices, and related methods |
US20080183279A1 (en) * | 2007-01-29 | 2008-07-31 | Cook Incorporated | Prosthetic Valve with Slanted Leaflet Design |
US20080183280A1 (en) * | 2007-01-29 | 2008-07-31 | Cook Incorporated | Artificial venous valve with discrete shaping members |
US20080262602A1 (en) * | 1998-09-10 | 2008-10-23 | Jenavalve Technology, Inc. | Methods and conduits for flowing blood from a heart chamber to a blood vessel |
US20090062907A1 (en) * | 2007-08-31 | 2009-03-05 | Quijano Rodolfo C | Self-expanding valve for the venous system |
US20090177270A1 (en) * | 2008-01-08 | 2009-07-09 | Cook Incorporated | Flow-Deflecting Prosthesis for Treating Venous Disease |
US20090222085A1 (en) * | 2008-02-22 | 2009-09-03 | University Of Iowa Research Foundation | Cellulose Based Heart Valve Prosthesis |
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 |
US20100100167A1 (en) * | 2008-10-17 | 2010-04-22 | Georg Bortlein | Delivery system for deployment of medical devices |
US20100114300A1 (en) * | 2004-12-01 | 2010-05-06 | Cook Incorporated | Medical device with leak path |
US7722666B2 (en) | 2005-04-15 | 2010-05-25 | Boston Scientific Scimed, Inc. | Valve apparatus, system and method |
US7776053B2 (en) | 2000-10-26 | 2010-08-17 | Boston Scientific Scimed, Inc. | Implantable valve system |
US7780627B2 (en) | 2002-12-30 | 2010-08-24 | Boston Scientific Scimed, Inc. | Valve treatment catheter and methods |
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 |
US7854761B2 (en) | 2003-12-19 | 2010-12-21 | Boston Scientific Scimed, Inc. | Methods for venous valve replacement with a catheter |
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 |
US7892276B2 (en) | 2007-12-21 | 2011-02-22 | Boston Scientific Scimed, Inc. | Valve with delayed leaflet deployment |
US7896915B2 (en) | 2007-04-13 | 2011-03-01 | Jenavalve Technology, Inc. | Medical device for treating a heart valve insufficiency |
US7896913B2 (en) | 2000-02-28 | 2011-03-01 | Jenavalve Technology, Inc. | Anchoring system for implantable heart valve prostheses |
US7951189B2 (en) | 2005-09-21 | 2011-05-31 | Boston Scientific Scimed, Inc. | Venous valve, system, and method with sinus pocket |
US7967853B2 (en) | 2007-02-05 | 2011-06-28 | Boston Scientific Scimed, Inc. | Percutaneous valve, system and method |
US7972378B2 (en) | 2008-01-24 | 2011-07-05 | Medtronic, Inc. | Stents for prosthetic heart valves |
US8002824B2 (en) | 2004-09-02 | 2011-08-23 | Boston Scientific Scimed, Inc. | Cardiac valve, system, and method |
US8012198B2 (en) | 2005-06-10 | 2011-09-06 | Boston Scientific Scimed, Inc. | Venous valve, system, and method |
US8016877B2 (en) | 1999-11-17 | 2011-09-13 | Medtronic Corevalve Llc | Prosthetic valve for transluminal delivery |
US8052749B2 (en) | 2003-12-23 | 2011-11-08 | Sadra Medical, Inc. | Methods and apparatus for endovascular heart valve replacement comprising tissue grasping elements |
US8062355B2 (en) | 2005-11-04 | 2011-11-22 | Jenavalve Technology, Inc. | Self-expandable medical instrument for treating defects in a patient's heart |
US8070801B2 (en) | 2001-06-29 | 2011-12-06 | Medtronic, Inc. | Method and apparatus for resecting and replacing an aortic valve |
US8092487B2 (en) | 2000-06-30 | 2012-01-10 | Medtronic, Inc. | Intravascular filter with debris entrapment mechanism |
US8092521B2 (en) | 2005-10-28 | 2012-01-10 | Jenavalve Technology, Inc. | Device for the implantation and fixation of prosthetic valves |
US8109996B2 (en) | 2004-03-03 | 2012-02-07 | Sorin Biomedica Cardio, S.R.L. | Minimally-invasive cardiac-valve prosthesis |
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 |
US8137398B2 (en) | 2008-10-13 | 2012-03-20 | Medtronic Ventor Technologies Ltd | Prosthetic valve having tapered tip when compressed for delivery |
US8157853B2 (en) | 2008-01-24 | 2012-04-17 | Medtronic, Inc. | Delivery systems and methods of implantation for prosthetic heart valves |
US8182528B2 (en) | 2003-12-23 | 2012-05-22 | Sadra Medical, Inc. | Locking heart valve anchor |
US8206437B2 (en) | 2001-08-03 | 2012-06-26 | Philipp Bonhoeffer | Implant implantation unit and procedure for implanting the unit |
US8226710B2 (en) | 2005-05-13 | 2012-07-24 | Medtronic Corevalve, Inc. | Heart valve prosthesis and methods of manufacture and use |
US8231670B2 (en) | 2003-12-23 | 2012-07-31 | Sadra Medical, Inc. | Repositionable heart valve and method |
US8246678B2 (en) | 2003-12-23 | 2012-08-21 | Sadra Medicl, Inc. | Methods and apparatus for endovascularly replacing a patient's heart valve |
US8252052B2 (en) | 2003-12-23 | 2012-08-28 | Sadra Medical, Inc. | Methods and apparatus for endovascularly replacing a patient's heart valve |
US8317858B2 (en) | 2008-02-26 | 2012-11-27 | Jenavalve Technology, Inc. | Stent for the positioning and anchoring of a valvular prosthesis in an implantation site in the heart of a patient |
US8328868B2 (en) | 2004-11-05 | 2012-12-11 | Sadra Medical, Inc. | Medical devices and delivery systems for delivering medical devices |
US8337545B2 (en) | 2004-02-09 | 2012-12-25 | Cook Medical Technologies Llc | Woven implantable device |
US8343213B2 (en) | 2003-12-23 | 2013-01-01 | Sadra Medical, Inc. | Leaflet engagement elements and methods for use thereof |
US8398704B2 (en) | 2008-02-26 | 2013-03-19 | Jenavalve Technology, Inc. | Stent for the positioning and anchoring of a valvular prosthesis in an implantation site in the heart of a patient |
US8414643B2 (en) | 2006-09-19 | 2013-04-09 | Medtronic Ventor Technologies Ltd. | Sinus-engaging valve fixation member |
US8430927B2 (en) | 2008-04-08 | 2013-04-30 | Medtronic, Inc. | Multiple orifice implantable heart valve and methods of implantation |
US8465540B2 (en) | 2008-02-26 | 2013-06-18 | Jenavalve Technology, Inc. | Stent for the positioning and anchoring of a valvular prosthesis |
US8468667B2 (en) | 2009-05-15 | 2013-06-25 | Jenavalve Technology, Inc. | Device for compressing a stent |
US8512397B2 (en) | 2009-04-27 | 2013-08-20 | Sorin Group Italia S.R.L. | Prosthetic vascular conduit |
US8539662B2 (en) | 2005-02-10 | 2013-09-24 | Sorin Group Italia S.R.L. | Cardiac-valve prosthesis |
US8579962B2 (en) | 2003-12-23 | 2013-11-12 | Sadra Medical, Inc. | Methods and apparatus for performing valvuloplasty |
US8603159B2 (en) | 1999-11-17 | 2013-12-10 | Medtronic Corevalve, Llc | Prosthetic valve for transluminal delivery |
US8603160B2 (en) | 2003-12-23 | 2013-12-10 | Sadra Medical, Inc. | Method of using a retrievable heart valve anchor with a sheath |
US8623076B2 (en) | 2003-12-23 | 2014-01-07 | Sadra Medical, Inc. | Low profile heart valve and delivery system |
US8623077B2 (en) | 2001-06-29 | 2014-01-07 | Medtronic, Inc. | Apparatus for replacing a cardiac valve |
US8652204B2 (en) | 2010-04-01 | 2014-02-18 | Medtronic, Inc. | Transcatheter valve with torsion spring fixation and related systems and methods |
US8668733B2 (en) | 2004-06-16 | 2014-03-11 | Sadra Medical, Inc. | Everting heart valve |
US8679174B2 (en) | 2005-01-20 | 2014-03-25 | JenaValve Technology, GmbH | Catheter for the transvascular implantation of prosthetic heart valves |
US8685084B2 (en) | 2011-12-29 | 2014-04-01 | Sorin Group Italia S.R.L. | Prosthetic vascular conduit and assembly method |
US8721714B2 (en) | 2008-09-17 | 2014-05-13 | Medtronic Corevalve Llc | Delivery system for deployment of medical devices |
US8721708B2 (en) | 1999-11-17 | 2014-05-13 | Medtronic Corevalve Llc | Prosthetic valve for transluminal delivery |
US8747459B2 (en) | 2006-12-06 | 2014-06-10 | Medtronic Corevalve Llc | System and method for transapical delivery of an annulus anchored self-expanding valve |
US20140163520A1 (en) * | 2009-04-09 | 2014-06-12 | Osseous Technologies Of America | Collagen biomaterial for containment of biomaterials |
US8771302B2 (en) | 2001-06-29 | 2014-07-08 | Medtronic, Inc. | Method and apparatus for resecting and replacing an aortic valve |
US8784478B2 (en) | 2006-10-16 | 2014-07-22 | Medtronic Corevalve, Inc. | Transapical delivery system with ventruculo-arterial overlfow bypass |
US8795319B2 (en) | 2011-03-02 | 2014-08-05 | Cook Medical Technologies Llc | Embolization coil |
US8808369B2 (en) | 2009-10-05 | 2014-08-19 | Mayo Foundation For Medical Education And Research | Minimally invasive aortic valve replacement |
US8828079B2 (en) | 2007-07-26 | 2014-09-09 | Boston Scientific Scimed, Inc. | Circulatory valve, system and method |
USRE45130E1 (en) | 2000-02-28 | 2014-09-09 | Jenavalve Technology Gmbh | Device for fastening and anchoring cardiac valve prostheses |
US8834563B2 (en) | 2008-12-23 | 2014-09-16 | Sorin Group Italia S.R.L. | Expandable prosthetic valve having anchoring appendages |
US8834564B2 (en) | 2006-09-19 | 2014-09-16 | Medtronic, Inc. | Sinus-engaging valve fixation member |
US8840663B2 (en) | 2003-12-23 | 2014-09-23 | Sadra Medical, Inc. | Repositionable heart valve method |
US8840661B2 (en) | 2008-05-16 | 2014-09-23 | Sorin Group Italia S.R.L. | Atraumatic prosthetic heart valve prosthesis |
US8858620B2 (en) | 2003-12-23 | 2014-10-14 | Sadra Medical Inc. | Methods and apparatus for endovascularly replacing a heart valve |
US8894703B2 (en) | 2003-12-23 | 2014-11-25 | Sadra Medical, Inc. | Systems and methods for delivering a medical implant |
US8951280B2 (en) | 2000-11-09 | 2015-02-10 | Medtronic, Inc. | Cardiac valve procedure methods and devices |
US8998976B2 (en) | 2011-07-12 | 2015-04-07 | Boston Scientific Scimed, Inc. | Coupling system for medical devices |
US8998981B2 (en) | 2008-09-15 | 2015-04-07 | Medtronic, Inc. | Prosthetic heart valve having identifiers for aiding in radiographic positioning |
US9005273B2 (en) | 2003-12-23 | 2015-04-14 | Sadra Medical, Inc. | Assessing the location and performance of replacement heart valves |
US9011521B2 (en) | 2003-12-23 | 2015-04-21 | Sadra Medical, Inc. | Methods and apparatus for endovascularly replacing a patient's heart valve |
US9044318B2 (en) | 2008-02-26 | 2015-06-02 | Jenavalve Technology Gmbh | Stent for the positioning and anchoring of a valvular prosthesis |
US9050264B2 (en) | 2009-11-07 | 2015-06-09 | University Of Iowa Research Foundation | Cellulose capsules and methods for making them |
US9132025B2 (en) | 2012-06-15 | 2015-09-15 | Trivascular, Inc. | Bifurcated endovascular prosthesis having tethered contralateral leg |
US9138315B2 (en) | 2007-04-13 | 2015-09-22 | Jenavalve Technology Gmbh | Medical device for treating a heart valve insufficiency or stenosis |
US9149358B2 (en) | 2008-01-24 | 2015-10-06 | Medtronic, Inc. | Delivery systems for prosthetic heart valves |
US9161836B2 (en) | 2011-02-14 | 2015-10-20 | Sorin Group Italia S.R.L. | Sutureless anchoring device for cardiac valve prostheses |
US9168130B2 (en) | 2008-02-26 | 2015-10-27 | Jenavalve Technology Gmbh | Stent for the positioning and anchoring of a valvular prosthesis in an implantation site in the heart of a patient |
US9226826B2 (en) | 2010-02-24 | 2016-01-05 | Medtronic, Inc. | Transcatheter valve structure and methods for valve delivery |
US9237886B2 (en) | 2007-04-20 | 2016-01-19 | Medtronic, Inc. | Implant for treatment of a heart valve, in particular a mitral valve, material including such an implant, and material for insertion thereof |
US9248017B2 (en) | 2010-05-21 | 2016-02-02 | Sorin Group Italia S.R.L. | Support device for valve prostheses and corresponding kit |
US9289289B2 (en) | 2011-02-14 | 2016-03-22 | Sorin Group Italia S.R.L. | Sutureless anchoring device for cardiac valve prostheses |
US9295551B2 (en) | 2007-04-13 | 2016-03-29 | Jenavalve Technology Gmbh | Methods of implanting an endoprosthesis |
US9370419B2 (en) | 2005-02-23 | 2016-06-21 | Boston Scientific Scimed, Inc. | Valve apparatus, system and method |
US9370421B2 (en) | 2011-12-03 | 2016-06-21 | Boston Scientific Scimed, Inc. | Medical device handle |
US9393115B2 (en) | 2008-01-24 | 2016-07-19 | Medtronic, Inc. | Delivery systems and methods of implantation for prosthetic heart valves |
US9415225B2 (en) | 2005-04-25 | 2016-08-16 | Cardiac Pacemakers, Inc. | Method and apparatus for pacing during revascularization |
US9504568B2 (en) | 2007-02-16 | 2016-11-29 | Medtronic, Inc. | Replacement prosthetic heart valves and methods of implantation |
US9510947B2 (en) | 2011-10-21 | 2016-12-06 | Jenavalve Technology, Inc. | Catheter system for introducing an expandable heart valve stent into the body of a patient |
US9526609B2 (en) | 2003-12-23 | 2016-12-27 | Boston Scientific Scimed, Inc. | Methods and apparatus for endovascularly replacing a patient's heart valve |
US9539088B2 (en) | 2001-09-07 | 2017-01-10 | Medtronic, Inc. | Fixation band for affixing a prosthetic heart valve to tissue |
US9579194B2 (en) | 2003-10-06 | 2017-02-28 | Medtronic ATS Medical, Inc. | Anchoring structure with concave landing zone |
US9597182B2 (en) | 2010-05-20 | 2017-03-21 | Jenavalve Technology Inc. | Catheter system for introducing an expandable stent into the body of a patient |
US9622859B2 (en) | 2005-02-01 | 2017-04-18 | Boston Scientific Scimed, Inc. | Filter system and method |
US9629718B2 (en) | 2013-05-03 | 2017-04-25 | Medtronic, Inc. | Valve delivery tool |
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 |
US9744037B2 (en) | 2013-03-15 | 2017-08-29 | California Institute Of Technology | Handle mechanism and functionality for repositioning and retrieval of transcatheter heart valves |
US9744031B2 (en) | 2010-05-25 | 2017-08-29 | Jenavalve Technology, Inc. | Prosthetic heart valve and endoprosthesis comprising a prosthetic heart valve and a stent |
US9775704B2 (en) | 2004-04-23 | 2017-10-03 | Medtronic3F Therapeutics, Inc. | Implantable valve prosthesis |
US9788942B2 (en) | 2015-02-03 | 2017-10-17 | Boston Scientific Scimed Inc. | Prosthetic heart valve having tubular seal |
US20170325938A1 (en) | 2016-05-16 | 2017-11-16 | Boston Scientific Scimed, Inc. | Replacement heart valve implant with invertible leaflets |
US9839515B2 (en) | 2005-12-22 | 2017-12-12 | Symetis, SA | Stent-valves for valve replacement and associated methods and systems for surgery |
US9848981B2 (en) | 2007-10-12 | 2017-12-26 | Mayo Foundation For Medical Education And Research | Expandable valve prosthesis with sealing mechanism |
US9861477B2 (en) | 2015-01-26 | 2018-01-09 | Boston Scientific Scimed Inc. | Prosthetic heart valve square leaflet-leaflet stitch |
US9867694B2 (en) | 2013-08-30 | 2018-01-16 | Jenavalve Technology Inc. | Radially collapsible frame for a prosthetic valve and method for manufacturing such a frame |
US9867699B2 (en) | 2008-02-26 | 2018-01-16 | Jenavalve Technology, Inc. | Endoprosthesis for implantation in the heart of a patient |
US9878127B2 (en) | 2012-05-16 | 2018-01-30 | Jenavalve Technology, Inc. | Catheter delivery system for heart valve prosthesis |
US9901445B2 (en) | 2014-11-21 | 2018-02-27 | Boston Scientific Scimed, Inc. | Valve locking mechanism |
US9918833B2 (en) | 2010-09-01 | 2018-03-20 | Medtronic Vascular Galway | Prosthetic valve support structure |
US10080652B2 (en) | 2015-03-13 | 2018-09-25 | Boston Scientific Scimed, Inc. | Prosthetic heart valve having an improved tubular seal |
US10136991B2 (en) | 2015-08-12 | 2018-11-27 | Boston Scientific Scimed Inc. | Replacement heart valve implant |
US10172708B2 (en) | 2012-01-25 | 2019-01-08 | Boston Scientific Scimed, Inc. | Valve assembly with a bioabsorbable gasket and a replaceable valve implant |
US10179041B2 (en) | 2015-08-12 | 2019-01-15 | Boston Scientific Scimed Icn. | Pinless release mechanism |
US10188516B2 (en) | 2007-08-20 | 2019-01-29 | Medtronic Ventor Technologies Ltd. | Stent loading tool and method for use thereof |
US10195392B2 (en) | 2015-07-02 | 2019-02-05 | Boston Scientific Scimed, Inc. | Clip-on catheter |
US10201417B2 (en) | 2015-02-03 | 2019-02-12 | Boston Scientific Scimed Inc. | Prosthetic heart valve having tubular seal |
US10201418B2 (en) | 2010-09-10 | 2019-02-12 | Symetis, SA | Valve replacement devices, delivery device for a valve replacement device and method of production of a valve replacement device |
US10258465B2 (en) | 2003-12-23 | 2019-04-16 | Boston Scientific Scimed Inc. | Methods and apparatus for endovascular heart valve replacement comprising tissue grasping elements |
US10278805B2 (en) | 2000-08-18 | 2019-05-07 | Atritech, Inc. | Expandable implant devices for filtering blood flow from atrial appendages |
US10285809B2 (en) | 2015-03-06 | 2019-05-14 | Boston Scientific Scimed Inc. | TAVI anchoring assist device |
US10335277B2 (en) | 2015-07-02 | 2019-07-02 | Boston Scientific Scimed Inc. | Adjustable nosecone |
US10342660B2 (en) | 2016-02-02 | 2019-07-09 | Boston Scientific Inc. | Tensioned sheathing aids |
US10426617B2 (en) | 2015-03-06 | 2019-10-01 | Boston Scientific Scimed, Inc. | Low profile valve locking mechanism and commissure assembly |
US10449043B2 (en) | 2015-01-16 | 2019-10-22 | Boston Scientific Scimed, Inc. | Displacement based lock and release mechanism |
US10555809B2 (en) | 2012-06-19 | 2020-02-11 | Boston Scientific Scimed, Inc. | Replacement heart valve |
US10583005B2 (en) | 2016-05-13 | 2020-03-10 | Boston Scientific Scimed, Inc. | Medical device handle |
US10709555B2 (en) | 2015-05-01 | 2020-07-14 | Jenavalve Technology, Inc. | Device and method with reduced pacemaker rate in heart valve replacement |
US10828154B2 (en) | 2017-06-08 | 2020-11-10 | Boston Scientific Scimed, Inc. | Heart valve implant commissure support structure |
US10856970B2 (en) | 2007-10-10 | 2020-12-08 | Medtronic Ventor Technologies Ltd. | Prosthetic heart valve for transfemoral delivery |
US10898325B2 (en) | 2017-08-01 | 2021-01-26 | Boston Scientific Scimed, Inc. | Medical implant locking mechanism |
US10939996B2 (en) | 2017-08-16 | 2021-03-09 | Boston Scientific Scimed, Inc. | Replacement heart valve commissure assembly |
US10940167B2 (en) | 2012-02-10 | 2021-03-09 | Cvdevices, Llc | Methods and uses of biological tissues for various stent and other medical applications |
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 |
US11147668B2 (en) | 2018-02-07 | 2021-10-19 | Boston Scientific Scimed, Inc. | Medical device delivery system with alignment feature |
US11191641B2 (en) | 2018-01-19 | 2021-12-07 | Boston Scientific Scimed, Inc. | Inductance mode deployment sensors for transcatheter valve system |
US11197754B2 (en) | 2017-01-27 | 2021-12-14 | Jenavalve Technology, Inc. | Heart valve mimicry |
US11229517B2 (en) | 2018-05-15 | 2022-01-25 | Boston Scientific Scimed, Inc. | Replacement heart valve commissure assembly |
US11241310B2 (en) | 2018-06-13 | 2022-02-08 | Boston Scientific Scimed, Inc. | Replacement heart valve delivery device |
US11241312B2 (en) | 2018-12-10 | 2022-02-08 | Boston Scientific Scimed, Inc. | Medical device delivery system including a resistance member |
US11246625B2 (en) | 2018-01-19 | 2022-02-15 | Boston Scientific Scimed, Inc. | Medical device delivery system with feedback loop |
US11278406B2 (en) | 2010-05-20 | 2022-03-22 | Jenavalve Technology, Inc. | Catheter system for introducing an expandable heart valve stent into the body of a patient, insertion system with a catheter system and medical device for treatment of a heart valve defect |
US11278398B2 (en) | 2003-12-23 | 2022-03-22 | Boston Scientific Scimed, Inc. | Methods and apparatus for endovascular heart valve replacement comprising tissue grasping elements |
US11285002B2 (en) | 2003-12-23 | 2022-03-29 | Boston Scientific Scimed, Inc. | Methods and apparatus for endovascularly replacing a heart valve |
US11304800B2 (en) | 2006-09-19 | 2022-04-19 | Medtronic Ventor Technologies Ltd. | Sinus-engaging valve fixation member |
US11406495B2 (en) | 2013-02-11 | 2022-08-09 | Cook Medical Technologies Llc | Expandable support frame and medical device |
US11439504B2 (en) | 2019-05-10 | 2022-09-13 | Boston Scientific Scimed, Inc. | Replacement heart valve with improved cusp washout and reduced loading |
US11439732B2 (en) | 2018-02-26 | 2022-09-13 | Boston Scientific Scimed, Inc. | Embedded radiopaque marker in adaptive seal |
US11504231B2 (en) | 2018-05-23 | 2022-11-22 | Corcym S.R.L. | Cardiac valve prosthesis |
US11771544B2 (en) | 2011-05-05 | 2023-10-03 | Symetis Sa | Method and apparatus for compressing/loading stent-valves |
US11826490B1 (en) | 2020-12-29 | 2023-11-28 | Acell, Inc. | Extracellular matrix sheet devices with improved mechanical properties and method of making |
US11969341B2 (en) | 2022-11-18 | 2024-04-30 | Corcym S.R.L. | Cardiac valve prosthesis |
Families Citing this family (480)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US6241747B1 (en) | 1993-05-03 | 2001-06-05 | Quill Medical, Inc. | Barbed Bodily tissue connector |
US8795332B2 (en) | 2002-09-30 | 2014-08-05 | Ethicon, Inc. | Barbed sutures |
US5931855A (en) | 1997-05-21 | 1999-08-03 | Frank Hoffman | Surgical methods using one-way suture |
US7452371B2 (en) * | 1999-06-02 | 2008-11-18 | Cook Incorporated | Implantable vascular device |
US8241274B2 (en) | 2000-01-19 | 2012-08-14 | Medtronic, Inc. | Method for guiding a medical device |
ES2286097T7 (en) * | 2000-01-31 | 2009-11-05 | Cook Biotech, Inc | ENDOPROTESIS VALVES. |
KR100786028B1 (en) * | 2000-02-03 | 2007-12-17 | 쿡 인코포레이티드 | Implantable vascular device |
AU2001245432B2 (en) * | 2000-03-03 | 2006-04-27 | Cook Medical Technologies Llc | Bulbous valve and stent for treating vascular reflux |
WO2004030568A2 (en) * | 2002-10-01 | 2004-04-15 | Ample Medical, Inc. | Device and method for repairing a native heart valve leaflet |
WO2002061658A2 (en) * | 2001-01-30 | 2002-08-08 | Personal Genie, Inc. | System and method for matching consumers with products |
AU2002254758A1 (en) * | 2001-04-30 | 2002-11-11 | Francisco J. Osse | Replacement venous valve |
US7056331B2 (en) | 2001-06-29 | 2006-06-06 | Quill Medical, Inc. | Suture method |
FR2826863B1 (en) | 2001-07-04 | 2003-09-26 | Jacques Seguin | ASSEMBLY FOR PLACING A PROSTHETIC VALVE IN A BODY CONDUIT |
FR2828091B1 (en) | 2001-07-31 | 2003-11-21 | Seguin Jacques | ASSEMBLY ALLOWING THE PLACEMENT OF A PROTHETIC VALVE IN A BODY DUCT |
US7288105B2 (en) | 2001-08-01 | 2007-10-30 | Ev3 Endovascular, Inc. | Tissue opening occluder |
US6848152B2 (en) | 2001-08-31 | 2005-02-01 | Quill Medical, Inc. | Method of forming barbs on a suture and apparatus for performing same |
US6776784B2 (en) | 2001-09-06 | 2004-08-17 | Core Medical, Inc. | Clip apparatus for closing septal defects and methods of use |
US6702835B2 (en) | 2001-09-07 | 2004-03-09 | Core Medical, Inc. | Needle apparatus for closing septal defects and methods for using such apparatus |
US20060052821A1 (en) | 2001-09-06 | 2006-03-09 | Ovalis, Inc. | Systems and methods for treating septal defects |
WO2003053493A2 (en) | 2001-12-19 | 2003-07-03 | Nmt Medical, Inc. | Septal occluder and associated methods |
US7318833B2 (en) | 2001-12-19 | 2008-01-15 | Nmt Medical, Inc. | PFO closure device with flexible thrombogenic joint and improved dislodgement resistance |
EP2135583B1 (en) * | 2001-12-20 | 2012-04-18 | TriVascular, Inc. | Advanced endovascular graft |
US7201771B2 (en) * | 2001-12-27 | 2007-04-10 | Arbor Surgical Technologies, Inc. | Bioprosthetic heart valve |
US7166124B2 (en) * | 2002-03-21 | 2007-01-23 | Providence Health System - Oregon | Method for manufacturing sutureless bioprosthetic stent |
US20070003653A1 (en) * | 2002-03-21 | 2007-01-04 | Ahle Karen M | Automated manufacturing device and method for biomaterial fusion |
US7163556B2 (en) * | 2002-03-21 | 2007-01-16 | Providence Health System - Oregon | Bioprosthesis and method for suturelessly making same |
WO2003082076A2 (en) | 2002-03-25 | 2003-10-09 | Nmt Medical, Inc. | Patent foramen ovale (pfo) closure clips |
US7125418B2 (en) * | 2002-04-16 | 2006-10-24 | The International Heart Institute Of Montana Foundation | Sigmoid valve and method for its percutaneous implantation |
US8721713B2 (en) | 2002-04-23 | 2014-05-13 | Medtronic, Inc. | System for implanting a replacement valve |
US6676699B2 (en) * | 2002-04-26 | 2004-01-13 | Medtronic Ave, Inc | Stent graft with integrated valve device and method |
CA2486919C (en) | 2002-06-03 | 2011-03-15 | Nmt Medical, Inc. | Device with biological tissue scaffold for percutaneous closure of an intracardiac defect and methods thereof |
US7431729B2 (en) | 2002-06-05 | 2008-10-07 | Nmt Medical, Inc. | Patent foramen ovale (PFO) closure device with radial and circumferential support |
US8348963B2 (en) * | 2002-07-03 | 2013-01-08 | Hlt, Inc. | Leaflet reinforcement for regurgitant valves |
US7166120B2 (en) * | 2002-07-12 | 2007-01-23 | Ev3 Inc. | Catheter with occluding cuff |
DE10233085B4 (en) | 2002-07-19 | 2014-02-20 | Dendron Gmbh | Stent with guide wire |
US6773450B2 (en) | 2002-08-09 | 2004-08-10 | Quill Medical, Inc. | Suture anchor and method |
US20040034407A1 (en) | 2002-08-16 | 2004-02-19 | John Sherry | Covered stents with degradable barbs |
CA2503258C (en) * | 2002-08-28 | 2011-08-16 | Heart Leaflet Technologies, Inc. | Method and device for treating diseased valve |
US6875231B2 (en) * | 2002-09-11 | 2005-04-05 | 3F Therapeutics, Inc. | Percutaneously deliverable heart valve |
AU2003267164A1 (en) | 2002-09-12 | 2004-04-30 | Cook Incorporated | Retrievable filter |
US7137184B2 (en) * | 2002-09-20 | 2006-11-21 | Edwards Lifesciences Corporation | Continuous heart valve support frame and method of manufacture |
US20040088003A1 (en) | 2002-09-30 | 2004-05-06 | Leung Jeffrey C. | Barbed suture in combination with surgical needle |
US8100940B2 (en) | 2002-09-30 | 2012-01-24 | Quill Medical, Inc. | Barb configurations for barbed sutures |
EP1562522B1 (en) * | 2002-10-01 | 2008-12-31 | Ample Medical, Inc. | Devices and systems for reshaping a heart valve annulus |
AU2003285943B2 (en) * | 2002-10-24 | 2008-08-21 | Boston Scientific Limited | Venous valve apparatus and method |
US7766820B2 (en) | 2002-10-25 | 2010-08-03 | Nmt Medical, Inc. | Expandable sheath tubing |
AU2003294682A1 (en) | 2002-12-09 | 2004-06-30 | Nmt Medical, Inc. | Septal closure devices |
US8551162B2 (en) | 2002-12-20 | 2013-10-08 | Medtronic, Inc. | Biologically implantable prosthesis |
CA2512986A1 (en) * | 2003-01-24 | 2004-08-12 | Applied Medical Resources Corporation | Internal tissue retractor |
US7780700B2 (en) | 2003-02-04 | 2010-08-24 | ev3 Endovascular, Inc | Patent foramen ovale closure system |
US7658747B2 (en) | 2003-03-12 | 2010-02-09 | Nmt Medical, Inc. | Medical device for manipulation of a medical implant |
EP2168536B1 (en) * | 2003-03-12 | 2016-04-27 | Cook Medical Technologies LLC | Prosthetic valve that permits retrograde flow |
WO2004082528A2 (en) * | 2003-03-17 | 2004-09-30 | Cook Incorporated | Vascular valve with removable support component |
US7909862B2 (en) * | 2003-03-19 | 2011-03-22 | Cook Medical Technologies Llc | Delivery systems and methods for deploying expandable intraluminal medical devices |
CH696185A5 (en) * | 2003-03-21 | 2007-02-15 | Afksendiyos Kalangos | Intraparietal reinforcement for aortic valve and reinforced valve has rod inserted in biological tissue or organic prosthesis with strut fixed to one end |
EP1610728B1 (en) * | 2003-04-01 | 2011-05-25 | Cook Incorporated | Percutaneously deployed vascular valves |
WO2004091449A1 (en) * | 2003-04-08 | 2004-10-28 | Cook Incorporated | Intraluminal support device with graft |
WO2004093745A1 (en) * | 2003-04-23 | 2004-11-04 | Cook Incorporated | Devices kits, and methods for placing multiple intraluminal medical devices in a body vessel |
US8221492B2 (en) * | 2003-04-24 | 2012-07-17 | Cook Medical Technologies | Artificial valve prosthesis with improved flow dynamics |
US7717952B2 (en) | 2003-04-24 | 2010-05-18 | Cook Incorporated | Artificial prostheses with preferred geometries |
US7625399B2 (en) | 2003-04-24 | 2009-12-01 | Cook Incorporated | Intralumenally-implantable frames |
US7624487B2 (en) | 2003-05-13 | 2009-12-01 | Quill Medical, Inc. | Apparatus and method for forming barbs on a suture |
US20040230289A1 (en) * | 2003-05-15 | 2004-11-18 | Scimed Life Systems, Inc. | Sealable attachment of endovascular stent to graft |
WO2004103222A1 (en) * | 2003-05-19 | 2004-12-02 | Cook Incorporated | Implantable medical device with constrained expansion |
WO2004103209A2 (en) | 2003-05-19 | 2004-12-02 | Secant Medical Llc | Tissue distention device and related methods for therapeutic intervention |
US9861346B2 (en) | 2003-07-14 | 2018-01-09 | W. L. Gore & Associates, Inc. | Patent foramen ovale (PFO) closure device with linearly elongating petals |
WO2005006990A2 (en) | 2003-07-14 | 2005-01-27 | Nmt Medical, Inc. | Tubular patent foramen ovale (pfo) closure device with catch system |
US8480706B2 (en) | 2003-07-14 | 2013-07-09 | W.L. Gore & Associates, Inc. | Tubular patent foramen ovale (PFO) closure device with catch system |
WO2005011535A2 (en) * | 2003-07-31 | 2005-02-10 | Cook Incorporated | Prosthetic valve for implantation in a body vessel |
US7963952B2 (en) | 2003-08-19 | 2011-06-21 | Wright Jr John A | Expandable sheath tubing |
US8021421B2 (en) | 2003-08-22 | 2011-09-20 | Medtronic, Inc. | Prosthesis heart valve fixturing device |
AU2004270239C1 (en) * | 2003-09-04 | 2011-07-07 | Cook Biotech Incorporated | Extracellular matrix composite materials, and manufacture and use thereof |
US20060259137A1 (en) * | 2003-10-06 | 2006-11-16 | Jason Artof | Minimally invasive valve replacement system |
US7056337B2 (en) * | 2003-10-21 | 2006-06-06 | Cook Incorporated | Natural tissue stent |
US7056286B2 (en) | 2003-11-12 | 2006-06-06 | Adrian Ravenscroft | Medical device anchor and delivery system |
US20050107867A1 (en) * | 2003-11-17 | 2005-05-19 | Taheri Syde A. | Temporary absorbable venous occlusive stent and superficial vein treatment method |
US20050113904A1 (en) * | 2003-11-25 | 2005-05-26 | Shank Peter J. | Composite stent with inner and outer stent elements and method of using the same |
US8435285B2 (en) | 2003-11-25 | 2013-05-07 | Boston Scientific Scimed, Inc. | Composite stent with inner and outer stent elements and method of using the same |
CA2547088C (en) * | 2003-11-28 | 2011-10-18 | Cook Biotech Incorporated | Vascular occlusion methods, systems and devices |
US20050273119A1 (en) | 2003-12-09 | 2005-12-08 | Nmt Medical, Inc. | Double spiral patent foramen ovale closure clamp |
EP2985006B1 (en) † | 2003-12-23 | 2019-06-19 | Boston Scientific Scimed, Inc. | Repositionable heart valve |
US7824443B2 (en) | 2003-12-23 | 2010-11-02 | Sadra Medical, Inc. | Medical implant delivery and deployment tool |
US7748389B2 (en) | 2003-12-23 | 2010-07-06 | Sadra Medical, Inc. | Leaflet engagement elements and methods for use thereof |
US7824442B2 (en) | 2003-12-23 | 2010-11-02 | Sadra Medical, Inc. | Methods and apparatus for endovascularly replacing a heart valve |
US8287584B2 (en) | 2005-11-14 | 2012-10-16 | Sadra Medical, Inc. | Medical implant deployment tool |
US7862610B2 (en) * | 2004-01-23 | 2011-01-04 | James Quintessenza | Bicuspid vascular valve and methods for making and implanting same |
US7320705B2 (en) * | 2004-01-23 | 2008-01-22 | James Quintessenza | Bicuspid pulmonary heart valve and method for making same |
US8262694B2 (en) | 2004-01-30 | 2012-09-11 | W.L. Gore & Associates, Inc. | Devices, systems, and methods for closure of cardiac openings |
US7470285B2 (en) * | 2004-02-05 | 2008-12-30 | Children's Medical Center Corp. | Transcatheter delivery of a replacement heart valve |
US8562505B2 (en) | 2004-02-20 | 2013-10-22 | The Children's Hospital Of Philadelphia | Uniform field magnetization and targeting of therapeutic formulations |
WO2005082289A1 (en) | 2004-02-20 | 2005-09-09 | Cook Incorporated | Prosthetic valve with spacing member |
US7846201B2 (en) * | 2004-02-20 | 2010-12-07 | The Children's Hospital Of Philadelphia | Magnetically-driven biodegradable gene delivery nanoparticles formulated with surface-attached polycationic complex |
US9028829B2 (en) * | 2004-02-20 | 2015-05-12 | The Children's Hospital Of Philadelphia | Uniform field magnetization and targeting of therapeutic formulations |
US8128692B2 (en) | 2004-02-27 | 2012-03-06 | Aortx, Inc. | Prosthetic heart valves, scaffolding structures, and systems and methods for implantation of same |
EP1737349A1 (en) | 2004-03-03 | 2007-01-03 | NMT Medical, Inc. | Delivery/recovery system for septal occluder |
US7449027B2 (en) * | 2004-03-29 | 2008-11-11 | Cook Incorporated | Modifying fluid flow in a body vessel lumen to promote intraluminal flow-sensitive processes |
WO2005094694A2 (en) * | 2004-03-29 | 2005-10-13 | Cook Biotech Incorporated | Medical graft products with differing regions and methods and systems for producing the same |
AU2005231356A1 (en) * | 2004-03-31 | 2005-10-20 | Med Institute, Inc. | Endoluminal graft with a prosthetic valve |
US8216299B2 (en) | 2004-04-01 | 2012-07-10 | Cook Medical Technologies Llc | Method to retract a body vessel wall with remodelable material |
US20050267524A1 (en) | 2004-04-09 | 2005-12-01 | Nmt Medical, Inc. | Split ends closure device |
US7582110B2 (en) * | 2004-04-13 | 2009-09-01 | Cook Incorporated | Implantable frame with variable compliance |
US20050240255A1 (en) * | 2004-04-23 | 2005-10-27 | Schaeffer Darin G | Carrier-Based Delivery System for Intraluminal Medical Devices |
US8361110B2 (en) | 2004-04-26 | 2013-01-29 | W.L. Gore & Associates, Inc. | Heart-shaped PFO closure device |
US8308760B2 (en) | 2004-05-06 | 2012-11-13 | W.L. Gore & Associates, Inc. | Delivery systems and methods for PFO closure device with two anchors |
US7842053B2 (en) | 2004-05-06 | 2010-11-30 | Nmt Medical, Inc. | Double coil occluder |
WO2005110240A1 (en) | 2004-05-07 | 2005-11-24 | Nmt Medical, Inc. | Catching mechanisms for tubular septal occluder |
US7704268B2 (en) | 2004-05-07 | 2010-04-27 | Nmt Medical, Inc. | Closure device with hinges |
SG164370A1 (en) | 2004-05-14 | 2010-09-29 | Quill Medical Inc | Suture methods and devices |
US8292938B2 (en) * | 2004-08-27 | 2012-10-23 | Cook Medical Technologies Llc | Placement of multiple intraluminal medical devices within a body vessel |
CA2578706A1 (en) | 2004-09-01 | 2006-03-16 | Cook Incorporated | Delivery system which facilitates hydration of an intraluminal medical device |
US20060052867A1 (en) | 2004-09-07 | 2006-03-09 | Medtronic, Inc | Replacement prosthetic heart valve, system and method of implant |
JP4589395B2 (en) * | 2004-09-10 | 2010-12-01 | クック インコーポレイテッド | Prosthetic valve with holes |
WO2006034436A2 (en) | 2004-09-21 | 2006-03-30 | Stout Medical Group, L.P. | Expandable support device and method of use |
US20060064174A1 (en) * | 2004-09-22 | 2006-03-23 | Reza Zadno | Implantable valves and methods of making the same |
CA2581677C (en) | 2004-09-24 | 2014-07-29 | Nmt Medical, Inc. | Occluder device double securement system for delivery/recovery of such occluder device |
US20060074352A1 (en) * | 2004-10-06 | 2006-04-06 | Case Brian C | Wireguide with indicia |
US7563276B2 (en) * | 2004-10-29 | 2009-07-21 | Cook Incorporated | Intraluminal medical device with cannula for controlled retrograde flow |
US7458987B2 (en) * | 2004-10-29 | 2008-12-02 | Cook Incorporated | Vascular valves having implanted and target configurations and methods of preparing the same |
US7905826B2 (en) * | 2004-11-03 | 2011-03-15 | Cook Incorporated | Methods for modifying vascular vessel walls |
US7387604B2 (en) * | 2004-11-03 | 2008-06-17 | Cook Incorporated | Methods for treating valve-associated regions of vascular vessels |
US8562672B2 (en) | 2004-11-19 | 2013-10-22 | Medtronic, Inc. | Apparatus for treatment of cardiac valves and method of its manufacture |
US20060116572A1 (en) * | 2004-12-01 | 2006-06-01 | Case Brian C | Sensing delivery system for intraluminal medical devices |
WO2006062976A2 (en) * | 2004-12-07 | 2006-06-15 | Cook Incorporated | Methods for modifying vascular vessel walls |
US20070032850A1 (en) * | 2004-12-16 | 2007-02-08 | Carlos Ruiz | Separable sheath and method for insertion of a medical device into a bodily vessel using a separable sheath |
US20060217802A1 (en) * | 2004-12-16 | 2006-09-28 | Carlos Ruiz | Heart valve and method for insertion of the heart valve into a bodily vessel |
WO2006066150A2 (en) * | 2004-12-16 | 2006-06-22 | Carlos Ruiz | Separable sheath and method of using |
US7854747B2 (en) * | 2005-01-03 | 2010-12-21 | Crux Biomedical, Inc. | Endoluminal filter |
US20060206139A1 (en) * | 2005-01-19 | 2006-09-14 | Tekulve Kurt J | Vascular occlusion device |
US7972354B2 (en) | 2005-01-25 | 2011-07-05 | Tyco Healthcare Group Lp | Method and apparatus for impeding migration of an implanted occlusive structure |
CZ2007547A3 (en) | 2005-03-01 | 2007-10-24 | Andrieu@Raymond | IIntraparietal reinforcement device for biological prosthesis of heart and reinforced aortic valve biological prosthesis per se |
US8303647B2 (en) * | 2005-03-03 | 2012-11-06 | Cook Medical Technologies Llc | Medical valve leaflet structures with peripheral region receptive to tissue ingrowth |
US20060241687A1 (en) * | 2005-03-16 | 2006-10-26 | Glaser Erik N | Septal occluder with pivot arms and articulating joints |
US20060217760A1 (en) * | 2005-03-17 | 2006-09-28 | Widomski David R | Multi-strand septal occluder |
EP1868507A1 (en) | 2005-03-18 | 2007-12-26 | NMT Medical, Inc. | Catch member for pfo occluder |
WO2006102063A2 (en) * | 2005-03-19 | 2006-09-28 | Cook Biotech Incorporated | Prosthetic implants including ecm composite material |
US8372113B2 (en) | 2005-03-24 | 2013-02-12 | W.L. Gore & Associates, Inc. | Curved arm intracardiac occluder |
US7513909B2 (en) | 2005-04-08 | 2009-04-07 | Arbor Surgical Technologies, Inc. | Two-piece prosthetic valves with snap-in connection and methods for use |
US20060276882A1 (en) | 2005-04-11 | 2006-12-07 | Cook Incorporated | Medical device including remodelable material attached to frame |
EP1887980B1 (en) * | 2005-05-17 | 2012-09-05 | Cook Medical Technologies LLC | Frameless valve prosthesis and system for its deployment |
US7238200B2 (en) * | 2005-06-03 | 2007-07-03 | Arbor Surgical Technologies, Inc. | Apparatus and methods for making leaflets and valve prostheses including such leaflets |
US8579936B2 (en) | 2005-07-05 | 2013-11-12 | ProMed, Inc. | Centering of delivery devices with respect to a septal defect |
WO2007009107A2 (en) | 2005-07-14 | 2007-01-18 | Stout Medical Group, P.L. | Expandable support device and method of use |
EP1912593A1 (en) * | 2005-07-27 | 2008-04-23 | 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 |
US8771340B2 (en) * | 2005-08-25 | 2014-07-08 | Cook Medical Technologies Llc | Methods and devices for the endoluminal deployment and securement of prostheses |
US8470022B2 (en) * | 2005-08-31 | 2013-06-25 | Cook Biotech Incorporated | Implantable valve |
US7846179B2 (en) | 2005-09-01 | 2010-12-07 | Ovalis, Inc. | Suture-based systems and methods for treating septal defects |
US7712606B2 (en) | 2005-09-13 | 2010-05-11 | Sadra Medical, Inc. | Two-part package for medical implant |
EP1945142B1 (en) | 2005-09-26 | 2013-12-25 | Medtronic, Inc. | Prosthetic cardiac and venous valves |
US7503928B2 (en) * | 2005-10-21 | 2009-03-17 | Cook Biotech Incorporated | Artificial valve with center leaflet attachment |
US8292946B2 (en) * | 2005-10-25 | 2012-10-23 | Boston Scientific Scimed, Inc. | Medical implants with limited resistance to migration |
US20070112423A1 (en) * | 2005-11-16 | 2007-05-17 | Chu Jack F | Devices and methods for treatment of venous valve insufficiency |
US9131999B2 (en) * | 2005-11-18 | 2015-09-15 | C.R. Bard Inc. | Vena cava filter with filament |
CA2668988A1 (en) | 2005-12-15 | 2007-09-07 | Georgia Tech Research Corporation | Systems and methods for enabling heart valve replacement |
US20070167981A1 (en) | 2005-12-22 | 2007-07-19 | Nmt Medical, Inc. | Catch members for occluder devices |
US7815923B2 (en) | 2005-12-29 | 2010-10-19 | Cook Biotech Incorporated | Implantable graft material |
US20070167745A1 (en) * | 2005-12-29 | 2007-07-19 | Cook Incorporated | Methods for delivering medical devices to a target implant site within a body vessel |
US9078781B2 (en) | 2006-01-11 | 2015-07-14 | Medtronic, Inc. | Sterile cover for compressible stents used in percutaneous device delivery systems |
CA2637450A1 (en) * | 2006-01-31 | 2007-08-09 | Cook Biotech Incorporated | Fistula grafts and related methods and systems for treating fistulae |
US8147541B2 (en) | 2006-02-27 | 2012-04-03 | Aortx, Inc. | Methods and devices for delivery of prosthetic heart valves and other prosthetics |
US8403981B2 (en) | 2006-02-27 | 2013-03-26 | CardiacMC, Inc. | Methods and devices for delivery of prosthetic heart valves and other prosthetics |
US7648527B2 (en) * | 2006-03-01 | 2010-01-19 | Cook Incorporated | Methods of reducing retrograde flow |
EP2004095B1 (en) | 2006-03-28 | 2019-06-12 | Medtronic, Inc. | Prosthetic cardiac valve formed from pericardium material and methods of making same |
US8551135B2 (en) | 2006-03-31 | 2013-10-08 | W.L. Gore & Associates, Inc. | Screw catch mechanism for PFO occluder and method of use |
US8870913B2 (en) | 2006-03-31 | 2014-10-28 | W.L. Gore & Associates, Inc. | Catch system with locking cap for patent foramen ovale (PFO) occluder |
JP2009532125A (en) | 2006-03-31 | 2009-09-10 | エヌエムティー メディカル, インコーポレイティッド | Deformable flap catch mechanism for occluder equipment |
US7740655B2 (en) | 2006-04-06 | 2010-06-22 | Medtronic Vascular, Inc. | Reinforced surgical conduit for implantation of a stented valve therein |
US9017361B2 (en) | 2006-04-20 | 2015-04-28 | Covidien Lp | Occlusive implant and methods for hollow anatomical structure |
US20090216320A1 (en) * | 2006-04-21 | 2009-08-27 | The Children's Hospital Of Philadelphia | Magnetic Gradient Targeting And Sequestering Of Therapeutic Formulations And Therapeutic Systems Thereof |
WO2007130881A2 (en) | 2006-04-29 | 2007-11-15 | Arbor Surgical Technologies, Inc. | Multiple component prosthetic heart valve assemblies and apparatus and methods for delivering them |
JP5542273B2 (en) | 2006-05-01 | 2014-07-09 | スタウト メディカル グループ,エル.ピー. | Expandable support device and method of use |
EP2020965B1 (en) * | 2006-05-04 | 2017-04-19 | Cook Medical Technologies LLC | Self-orienting delivery system |
US8585594B2 (en) | 2006-05-24 | 2013-11-19 | Phoenix Biomedical, Inc. | Methods of assessing inner surfaces of body lumens or organs |
US8092517B2 (en) * | 2006-05-25 | 2012-01-10 | 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 |
EP3400908B1 (en) * | 2006-05-30 | 2020-06-17 | Cook Medical Technologies LLC | Artificial valve prosthesis |
US7867283B2 (en) * | 2006-05-30 | 2011-01-11 | Boston Scientific Scimed, Inc. | Anti-obesity diverter structure |
AU2007260928A1 (en) * | 2006-06-20 | 2007-12-27 | Aortx, Inc. | Prosthetic heart valves, support structures and systems and methods for implanting the same |
EP2035723A4 (en) | 2006-06-20 | 2011-11-30 | Aortx Inc | Torque shaft and torque drive |
JP5269779B2 (en) | 2006-06-21 | 2013-08-21 | クック・バイオテック・インコーポレーテッド | Acupuncture grafts and related methods and systems useful for the treatment of gastrointestinal fistulas |
AU2007260951A1 (en) | 2006-06-21 | 2007-12-27 | Aortx, Inc. | Prosthetic valve implantation systems |
US9408607B2 (en) | 2009-07-02 | 2016-08-09 | Edwards Lifesciences Cardiaq Llc | Surgical implant devices and methods for their manufacture and use |
US8252036B2 (en) | 2006-07-31 | 2012-08-28 | Syntheon Cardiology, Llc | Sealable endovascular implants and methods for their use |
US9585743B2 (en) | 2006-07-31 | 2017-03-07 | Edwards Lifesciences Cardiaq Llc | Surgical implant devices and methods for their manufacture and use |
US8439952B2 (en) * | 2006-08-04 | 2013-05-14 | Integrity Intellect, Inc. | Connecting rod for bone anchors having a bioresorbable tip |
US8894682B2 (en) * | 2006-09-11 | 2014-11-25 | Boston Scientific Scimed, Inc. | PFO clip |
FR2906998B1 (en) * | 2006-10-16 | 2009-04-10 | Perouse Soc Par Actions Simpli | IMPLANT INTENDED TO BE PLACED IN A BLOOD CIRCULATION CONDUIT. |
US20080147181A1 (en) | 2006-12-19 | 2008-06-19 | Sorin Biomedica Cardio S.R.L. | Device for in situ axial and radial positioning of cardiac valve prostheses |
US8070799B2 (en) | 2006-12-19 | 2011-12-06 | Sorin Biomedica Cardio S.R.L. | Instrument and method for in situ deployment of cardiac valve prostheses |
US8105375B2 (en) * | 2007-01-19 | 2012-01-31 | The Cleveland Clinic Foundation | Method for implanting a cardiovascular valve |
US20150335415A1 (en) | 2007-01-31 | 2015-11-26 | Stanley Batiste | Intravenous filter with guidewire and catheter access guide |
WO2008094706A2 (en) | 2007-02-01 | 2008-08-07 | Cook Incorporated | Closure device and method of closing a bodily opening |
US8617205B2 (en) | 2007-02-01 | 2013-12-31 | Cook Medical Technologies Llc | Closure device |
US20080188887A1 (en) * | 2007-02-07 | 2008-08-07 | Stanley Batiste | Removable vascular filter and method of filter placement |
ATE515244T1 (en) * | 2007-02-15 | 2011-07-15 | Cook Inc | ARTIFICIAL VALVE PROSTHESIS WITH FREE LEAF SECTION |
US8070802B2 (en) * | 2007-02-23 | 2011-12-06 | The Trustees Of The University Of Pennsylvania | Mitral valve system |
US9005242B2 (en) | 2007-04-05 | 2015-04-14 | W.L. Gore & Associates, Inc. | Septal closure device with centering mechanism |
US8915943B2 (en) | 2007-04-13 | 2014-12-23 | Ethicon, Inc. | Self-retaining systems for surgical procedures |
WO2008131167A1 (en) | 2007-04-18 | 2008-10-30 | Nmt Medical, Inc. | Flexible catheter system |
WO2008131405A1 (en) * | 2007-04-23 | 2008-10-30 | Cerebro Dynamics, Inc. | Securement device for shunt catheter and implantation method therefor |
US7815677B2 (en) | 2007-07-09 | 2010-10-19 | Leman Cardiovascular Sa | Reinforcement device for a biological valve and reinforced biological valve |
US8814847B2 (en) * | 2007-07-13 | 2014-08-26 | Cook Medical Technologies Llc | Delivery system for percutaneous placement of a medical device and method of use thereof |
US9814611B2 (en) | 2007-07-31 | 2017-11-14 | Edwards Lifesciences Cardiaq Llc | Actively controllable stent, stent graft, heart valve and method of controlling same |
US9566178B2 (en) | 2010-06-24 | 2017-02-14 | Edwards Lifesciences Cardiaq Llc | Actively controllable stent, stent graft, heart valve and method of controlling same |
ATE555752T1 (en) | 2007-08-24 | 2012-05-15 | St Jude Medical | AORTIC VALVE PROSTHESIS |
US8734483B2 (en) | 2007-08-27 | 2014-05-27 | Cook Medical Technologies Llc | Spider PFO closure device |
US8025495B2 (en) * | 2007-08-27 | 2011-09-27 | Cook Medical Technologies Llc | Apparatus and method for making a spider occlusion device |
US8308752B2 (en) * | 2007-08-27 | 2012-11-13 | Cook Medical Technologies Llc | Barrel occlusion device |
US8114154B2 (en) | 2007-09-07 | 2012-02-14 | Sorin Biomedica Cardio S.R.L. | Fluid-filled delivery system for in situ deployment of cardiac valve prostheses |
US8808367B2 (en) | 2007-09-07 | 2014-08-19 | Sorin Group Italia S.R.L. | Prosthetic valve delivery system including retrograde/antegrade approach |
WO2009036250A1 (en) | 2007-09-12 | 2009-03-19 | Cook Incorporated | Enhanced remodelable materials for occluding bodily vessels and related methods and systems |
AU2008305600B2 (en) | 2007-09-26 | 2013-07-04 | St. Jude Medical, Inc. | Collapsible prosthetic heart valves |
US8663309B2 (en) | 2007-09-26 | 2014-03-04 | Trivascular, Inc. | Asymmetric stent apparatus and method |
US8066755B2 (en) | 2007-09-26 | 2011-11-29 | Trivascular, Inc. | System and method of pivoted stent deployment |
US8226701B2 (en) | 2007-09-26 | 2012-07-24 | Trivascular, Inc. | Stent and delivery system for deployment thereof |
US8777987B2 (en) | 2007-09-27 | 2014-07-15 | Ethicon, Inc. | Self-retaining sutures including tissue retainers having improved strength |
US9532868B2 (en) | 2007-09-28 | 2017-01-03 | St. Jude Medical, Inc. | Collapsible-expandable prosthetic heart valves with structures for clamping native tissue |
WO2009045334A1 (en) | 2007-09-28 | 2009-04-09 | St. Jude Medical, Inc. | Collapsible/expandable prosthetic heart valves with native calcified leaflet retention features |
JP2010540190A (en) | 2007-10-04 | 2010-12-24 | トリバスキュラー・インコーポレイテッド | Modular vascular graft for low profile transdermal delivery |
US20090105813A1 (en) | 2007-10-17 | 2009-04-23 | Sean Chambers | Implantable valve device |
WO2009052207A2 (en) | 2007-10-17 | 2009-04-23 | Hancock Jaffe Laboratories | Biological valve for venous valve insufficiency |
US8328861B2 (en) | 2007-11-16 | 2012-12-11 | Trivascular, Inc. | Delivery system and method for bifurcated graft |
US8083789B2 (en) | 2007-11-16 | 2011-12-27 | Trivascular, Inc. | Securement assembly and method for expandable endovascular device |
US7846199B2 (en) * | 2007-11-19 | 2010-12-07 | Cook Incorporated | Remodelable prosthetic valve |
BRPI0704464A2 (en) * | 2007-11-30 | 2009-07-28 | Melchiades Da Cunha Neto | endoprosthesis, delivery system within a patient's vessel and uses of said delivery system and said endoprosthesis |
US20090149946A1 (en) * | 2007-12-05 | 2009-06-11 | Cook Incorporated | Stent having at least one barb and methods of manufacture |
US8257434B2 (en) | 2007-12-18 | 2012-09-04 | Cormatrix Cardiovascular, Inc. | Prosthetic tissue valve |
US8679176B2 (en) | 2007-12-18 | 2014-03-25 | Cormatrix Cardiovascular, Inc | Prosthetic tissue valve |
US8916077B1 (en) | 2007-12-19 | 2014-12-23 | Ethicon, Inc. | Self-retaining sutures with retainers formed from molten material |
US8771313B2 (en) | 2007-12-19 | 2014-07-08 | Ethicon, Inc. | Self-retaining sutures with heat-contact mediated retainers |
US8118834B1 (en) | 2007-12-20 | 2012-02-21 | Angiotech Pharmaceuticals, Inc. | Composite self-retaining sutures and method |
US20150164630A1 (en) * | 2008-01-04 | 2015-06-18 | Eric Johnson | Filter support members |
US20150173884A1 (en) * | 2008-01-04 | 2015-06-25 | Eric Johnson | Extended anchor endoluminal filter |
US8211165B1 (en) | 2008-01-08 | 2012-07-03 | Cook Medical Technologies Llc | Implantable device for placement in a vessel having a variable size |
WO2009091509A1 (en) | 2008-01-16 | 2009-07-23 | St. Jude Medical, Inc. | Delivery and retrieval systems for collapsible/expandable prosthetic heart valves |
EP2254513B1 (en) | 2008-01-24 | 2015-10-28 | Medtronic, Inc. | Stents for prosthetic heart valves |
WO2009094501A1 (en) | 2008-01-24 | 2009-07-30 | Medtronic, Inc. | Markers for prosthetic heart valves |
US8615856B1 (en) | 2008-01-30 | 2013-12-31 | Ethicon, Inc. | Apparatus and method for forming self-retaining sutures |
EP2242430B1 (en) | 2008-01-30 | 2016-08-17 | Ethicon, LLC | Apparatus and method for forming self-retaining sutures |
WO2009105663A2 (en) | 2008-02-21 | 2009-08-27 | Angiotech Pharmaceuticals, Inc. | Method and apparatus for elevating retainers on self-retaining sutures |
US8216273B1 (en) | 2008-02-25 | 2012-07-10 | Ethicon, Inc. | Self-retainers with supporting structures on a suture |
US8641732B1 (en) | 2008-02-26 | 2014-02-04 | Ethicon, Inc. | Self-retaining suture with variable dimension filament and method |
US20090264989A1 (en) | 2008-02-28 | 2009-10-22 | Philipp Bonhoeffer | Prosthetic heart valve systems |
US20130165967A1 (en) | 2008-03-07 | 2013-06-27 | W.L. Gore & Associates, Inc. | Heart occlusion devices |
US8313525B2 (en) | 2008-03-18 | 2012-11-20 | Medtronic Ventor Technologies, Ltd. | Valve suturing and implantation procedures |
ATE507801T1 (en) * | 2008-03-27 | 2011-05-15 | Ab Medica Spa | VALVE PROSTHESIS FOR IMPLANTATION IN BODY VESSELS |
JP5619726B2 (en) | 2008-04-15 | 2014-11-05 | エシコン・エルエルシーEthicon, LLC | Self-retaining suture with bidirectional retainer or unidirectional retainer |
US8128686B2 (en) * | 2008-04-18 | 2012-03-06 | Cook Medical Technologies Llc | Branched vessel prosthesis |
US8312825B2 (en) | 2008-04-23 | 2012-11-20 | Medtronic, Inc. | Methods and apparatuses for assembly of a pericardial prosthetic heart valve |
US8696743B2 (en) | 2008-04-23 | 2014-04-15 | Medtronic, Inc. | Tissue attachment devices and methods for prosthetic heart valves |
US8961560B2 (en) | 2008-05-16 | 2015-02-24 | Ethicon, Inc. | Bidirectional self-retaining sutures with laser-marked and/or non-laser marked indicia and methods |
AU2009251335A1 (en) * | 2008-05-29 | 2009-12-03 | Cook Biotech Incorporated | Devices and methods for treating rectovaginal and other fistulae |
US8323335B2 (en) * | 2008-06-20 | 2012-12-04 | Edwards Lifesciences Corporation | Retaining mechanisms for prosthetic valves and methods for using |
DE202009019058U1 (en) | 2008-07-15 | 2016-01-26 | St. Jude Medical, Inc. | Heart valve prosthesis and arrangement for delivering a heart valve prosthesis |
US9039756B2 (en) | 2008-07-21 | 2015-05-26 | Jenesis Surgical, Llc | Repositionable endoluminal support structure and its applications |
EP3878408A1 (en) | 2008-07-21 | 2021-09-15 | Jenesis Surgical, LLC | Endoluminal support apparatus |
WO2010011878A2 (en) * | 2008-07-24 | 2010-01-28 | Cook Incorporated | Valve device with biased leaflets |
JP2012501737A (en) * | 2008-09-03 | 2012-01-26 | クック・インコーポレイテッド | Hernia patch with removable elastic element |
US8986338B2 (en) * | 2008-10-29 | 2015-03-24 | Cook Biotech Incorporated | Vascular plugs |
AU2009319965B2 (en) | 2008-11-03 | 2014-11-06 | Ethicon Llc | Length of self-retaining suture and method and device for using the same |
US20100211176A1 (en) | 2008-11-12 | 2010-08-19 | Stout Medical Group, L.P. | Fixation device and method |
US20100204795A1 (en) | 2008-11-12 | 2010-08-12 | Stout Medical Group, L.P. | Fixation device and method |
US20100174363A1 (en) * | 2009-01-07 | 2010-07-08 | Endovalve, Inc. | One Piece Prosthetic Valve Support Structure and Related Assemblies |
US20130268062A1 (en) | 2012-04-05 | 2013-10-10 | Zeus Industrial Products, Inc. | Composite prosthetic devices |
PL3000472T3 (en) * | 2009-02-18 | 2017-09-29 | Cormatrix Cardiovascular, Inc. | Compositions for preventing atrial and ventricular fibrillation |
EP2405863B1 (en) * | 2009-02-24 | 2019-11-13 | Cook Medical Technologies LLC | Low profile support frame and related intraluminal medical devices |
AU2010218384B2 (en) | 2009-02-27 | 2014-11-20 | St. Jude Medical, Inc. | Stent features for collapsible prosthetic heart valves |
JP5693475B2 (en) * | 2009-03-04 | 2015-04-01 | ペイタント・ソリューションズ・インコーポレイテッドPeytant Solutions, Inc. | Stent modified with a material comprising amnion tissue and corresponding method |
US8029534B2 (en) | 2009-03-16 | 2011-10-04 | Cook Medical Technologies Llc | Closure device with string retractable umbrella |
EP2250975B1 (en) | 2009-05-13 | 2013-02-27 | Sorin Biomedica Cardio S.r.l. | Device for the in situ delivery of heart valves |
US9168105B2 (en) | 2009-05-13 | 2015-10-27 | Sorin Group Italia S.R.L. | Device for surgical interventions |
US8353953B2 (en) | 2009-05-13 | 2013-01-15 | Sorin Biomedica Cardio, S.R.L. | Device for the in situ delivery of heart valves |
US20120029556A1 (en) | 2009-06-22 | 2012-02-02 | Masters Steven J | Sealing device and delivery system |
US8956389B2 (en) | 2009-06-22 | 2015-02-17 | W. L. Gore & Associates, Inc. | Sealing device and delivery system |
US8845722B2 (en) * | 2009-08-03 | 2014-09-30 | Shlomo Gabbay | Heart valve prosthesis and method of implantation thereof |
JP5456892B2 (en) | 2009-08-07 | 2014-04-02 | ゼウス インダストリアル プロダクツ インコーポレイテッド | Multilayer composite |
EP2496189A4 (en) | 2009-11-04 | 2016-05-11 | Nitinol Devices And Components Inc | Alternating circumferential bridge stent design and methods for use thereof |
ES2365317B1 (en) | 2010-03-19 | 2012-08-03 | Xavier Ruyra Baliarda | PROTESTIC BAND, IN PARTICULAR FOR THE REPAIR OF A MITRAL VALVE. |
EP2549959A4 (en) * | 2010-03-22 | 2016-12-14 | Scitech Produtos Medicos Ltda | Endoprosthesis and delivery system for delivering the endoprosthesis within a vessel of a patient |
KR101066569B1 (en) * | 2010-04-06 | 2011-09-21 | 주식회사 리브라하트 | Polymer valve and pulsatile conduit-type vad using the same |
BR112012028331B1 (en) | 2010-05-04 | 2020-04-28 | Ethicon Endo Surgery Llc | self-retaining suture |
CN103068323B (en) | 2010-06-11 | 2015-07-22 | 伊西康有限责任公司 | Suture delivery tools for endoscopic and robot-assisted surgery and methods |
WO2011159342A1 (en) | 2010-06-17 | 2011-12-22 | St. Jude Medical, Inc. | Collapsible heart valve with angled frame |
US9039759B2 (en) | 2010-08-24 | 2015-05-26 | St. Jude Medical, Cardiology Division, Inc. | Repositioning of prosthetic heart valve and deployment |
EP2608741A2 (en) | 2010-08-24 | 2013-07-03 | St. Jude Medical, Inc. | Staged deployment devices and methods for transcatheter heart valve delivery systems |
EP2608747A4 (en) | 2010-08-24 | 2015-02-11 | Flexmedex Llc | Support device and method for use |
US8778019B2 (en) | 2010-09-17 | 2014-07-15 | St. Jude Medical, Cardiology Division, Inc. | Staged deployment devices and method for transcatheter heart valve delivery |
USD660433S1 (en) | 2010-09-20 | 2012-05-22 | St. Jude Medical, Inc. | Surgical stent assembly |
JP2013540484A (en) | 2010-09-20 | 2013-11-07 | セント・ジュード・メディカル,カーディオロジー・ディヴィジョン,インコーポレイテッド | Valve leaflet mounting device in foldable artificial valve |
USD652927S1 (en) | 2010-09-20 | 2012-01-24 | St. Jude Medical, Inc. | Surgical stent |
USD652926S1 (en) | 2010-09-20 | 2012-01-24 | St. Jude Medical, Inc. | Forked end |
USD654169S1 (en) | 2010-09-20 | 2012-02-14 | St. Jude Medical Inc. | Forked ends |
USD653343S1 (en) | 2010-09-20 | 2012-01-31 | St. Jude Medical, Inc. | Surgical cuff |
USD654170S1 (en) | 2010-09-20 | 2012-02-14 | St. Jude Medical, Inc. | Stent connections |
USD660967S1 (en) | 2010-09-20 | 2012-05-29 | St. Jude Medical, Inc. | Surgical stent |
USD684692S1 (en) | 2010-09-20 | 2013-06-18 | St. Jude Medical, Inc. | Forked ends |
USD648854S1 (en) | 2010-09-20 | 2011-11-15 | St. Jude Medical, Inc. | Commissure points |
USD653341S1 (en) | 2010-09-20 | 2012-01-31 | St. Jude Medical, Inc. | Surgical stent |
USD660432S1 (en) | 2010-09-20 | 2012-05-22 | St. Jude Medical, Inc. | Commissure point |
USD653342S1 (en) | 2010-09-20 | 2012-01-31 | St. Jude Medical, Inc. | Stent connections |
EP2624791B1 (en) | 2010-10-08 | 2017-06-21 | Confluent Medical Technologies, Inc. | Alternating circumferential bridge stent design |
US20120095542A1 (en) * | 2010-10-15 | 2012-04-19 | Cook Incorporated | Intraluminal medical device |
EP2627265B8 (en) | 2010-10-15 | 2019-02-20 | Cook Medical Technologies LLC | Occlusion device for blocking fluid flow through bodily passages |
GB201017921D0 (en) † | 2010-10-22 | 2010-12-01 | Ucl Business Plc | Prothesis delivery system |
CN103747746B (en) | 2010-11-03 | 2017-05-10 | 伊西康有限责任公司 | Drug-eluting self-retaining sutures and methods relating thereto |
RU2580479C2 (en) | 2010-11-09 | 2016-04-10 | ЭТИКОН ЭлЭлСи | Emergency self-retaining sutures and packaging therefor |
US9149286B1 (en) | 2010-11-12 | 2015-10-06 | Flexmedex, LLC | Guidance tool and method for use |
US10617514B2 (en) | 2010-12-22 | 2020-04-14 | W. L. Gore & Associates, Inc. | Biased endoluminal device |
US9155612B2 (en) | 2011-01-10 | 2015-10-13 | Intermountain Invention Management, Llc | Composite stent grafts for in situ assembly and related methods |
US9717593B2 (en) | 2011-02-01 | 2017-08-01 | St. Jude Medical, Cardiology Division, Inc. | Leaflet suturing to commissure points for prosthetic heart valve |
WO2012127309A1 (en) | 2011-03-21 | 2012-09-27 | Ontorfano Matteo | Disk-based valve apparatus and method for the treatment of valve dysfunction |
AU2012230716B2 (en) | 2011-03-23 | 2016-05-19 | Ethicon Llc | Self-retaining variable loop sutures |
US20120303048A1 (en) | 2011-05-24 | 2012-11-29 | Sorin Biomedica Cardio S.R.I. | Transapical valve replacement |
JP2014533119A (en) | 2011-05-27 | 2014-12-11 | コーマトリックス カーディオバスキュラー, インコーポレイテッドCorMatrix Cardiovascular, Inc. | Valve conduit for extracellular matrix material and method for making the same |
US20130172931A1 (en) | 2011-06-06 | 2013-07-04 | Jeffrey M. Gross | Methods and devices for soft palate tissue elevation procedures |
WO2013016275A1 (en) | 2011-07-22 | 2013-01-31 | Cook Medical Technologies Llc | Irrigation devices adapted to be used with a light source for the identification and treatment of bodily passages |
CA2855943C (en) | 2011-07-29 | 2019-10-29 | Carnegie Mellon University | Artificial valved conduits for cardiac reconstructive procedures and methods for their production |
US9770232B2 (en) | 2011-08-12 | 2017-09-26 | W. L. Gore & Associates, Inc. | Heart occlusion devices |
US9060860B2 (en) | 2011-08-18 | 2015-06-23 | St. Jude Medical, Cardiology Division, Inc. | Devices and methods for transcatheter heart valve delivery |
JP2014529445A (en) | 2011-08-23 | 2014-11-13 | フレックスメデックス,エルエルシー | Tissue removal apparatus and method |
US9827093B2 (en) | 2011-10-21 | 2017-11-28 | Edwards Lifesciences Cardiaq Llc | Actively controllable stent, stent graft, heart valve and method of controlling same |
US9131926B2 (en) | 2011-11-10 | 2015-09-15 | Boston Scientific Scimed, Inc. | Direct connect flush system |
US8940014B2 (en) | 2011-11-15 | 2015-01-27 | Boston Scientific Scimed, Inc. | Bond between components of a medical device |
WO2013076724A2 (en) * | 2011-11-21 | 2013-05-30 | Mor Research Applications Ltd. | Device for placement in the tricuspid annulus |
US9510945B2 (en) | 2011-12-20 | 2016-12-06 | Boston Scientific Scimed Inc. | Medical device handle |
US9277993B2 (en) | 2011-12-20 | 2016-03-08 | Boston Scientific Scimed, Inc. | Medical device delivery systems |
US10426501B2 (en) | 2012-01-13 | 2019-10-01 | Crux Biomedical, Inc. | Retrieval snare device and method |
US10213288B2 (en) | 2012-03-06 | 2019-02-26 | Crux Biomedical, Inc. | Distal protection filter |
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 |
US20130310927A1 (en) * | 2012-05-18 | 2013-11-21 | James Quintessenza | Implantable Valve System |
US9289292B2 (en) | 2012-06-28 | 2016-03-22 | St. Jude Medical, Cardiology Division, Inc. | Valve cuff support |
US9554902B2 (en) | 2012-06-28 | 2017-01-31 | St. Jude Medical, Cardiology Division, Inc. | Leaflet in configuration for function in various shapes and sizes |
US20140005776A1 (en) | 2012-06-29 | 2014-01-02 | St. Jude Medical, Cardiology Division, Inc. | Leaflet attachment for function in various shapes and sizes |
US9241791B2 (en) | 2012-06-29 | 2016-01-26 | St. Jude Medical, Cardiology Division, Inc. | Valve assembly for crimp profile |
US9615920B2 (en) | 2012-06-29 | 2017-04-11 | St. Jude Medical, Cardiology Divisions, Inc. | Commissure attachment feature for prosthetic heart valve |
US10004597B2 (en) | 2012-07-03 | 2018-06-26 | St. Jude Medical, Cardiology Division, Inc. | Stent and implantable valve incorporating same |
US9808342B2 (en) | 2012-07-03 | 2017-11-07 | St. Jude Medical, Cardiology Division, Inc. | Balloon sizing device and method of positioning a prosthetic heart valve |
AU2013292413B2 (en) | 2012-07-20 | 2017-02-02 | Cook Medical Technologies Llc | Implantable medical device having a sleeve |
US9339309B1 (en) | 2012-10-11 | 2016-05-17 | Nuvasive, Inc. | Systems and methods for inserting cross-connectors |
US10524909B2 (en) | 2012-10-12 | 2020-01-07 | St. Jude Medical, Cardiology Division, Inc. | Retaining cage to permit resheathing of a tavi aortic-first transapical system |
US9801721B2 (en) | 2012-10-12 | 2017-10-31 | St. Jude Medical, Cardiology Division, Inc. | Sizing device and method of positioning a prosthetic heart valve |
CA2896333C (en) | 2012-12-27 | 2021-01-12 | Transcatheter Technologies Gmbh | Apparatus and set for folding or unfolding a medical implant comprising a clamping mechanism |
WO2014110209A1 (en) * | 2013-01-09 | 2014-07-17 | Cook Medical Technologies Llc | Abdominal retractor |
US10828019B2 (en) | 2013-01-18 | 2020-11-10 | W.L. Gore & Associates, Inc. | Sealing device and delivery system |
US9314163B2 (en) | 2013-01-29 | 2016-04-19 | St. Jude Medical, Cardiology Division, Inc. | Tissue sensing device for sutureless valve selection |
US9186238B2 (en) | 2013-01-29 | 2015-11-17 | St. Jude Medical, Cardiology Division, Inc. | Aortic great vessel protection |
US9655719B2 (en) | 2013-01-29 | 2017-05-23 | St. Jude Medical, Cardiology Division, Inc. | Surgical heart valve flexible stent frame stiffener |
AU2014214811B2 (en) | 2013-02-08 | 2018-02-22 | Muffin Incorporated | Peripheral sealing venous check-valve |
US9895055B2 (en) | 2013-02-28 | 2018-02-20 | Cook Medical Technologies Llc | Medical devices, systems, and methods for the visualization and treatment of bodily passages |
US9901470B2 (en) | 2013-03-01 | 2018-02-27 | St. Jude Medical, Cardiology Division, Inc. | Methods of repositioning a transcatheter heart valve after full deployment |
US9844435B2 (en) | 2013-03-01 | 2017-12-19 | St. Jude Medical, Cardiology Division, Inc. | Transapical mitral valve replacement |
US9480563B2 (en) | 2013-03-08 | 2016-11-01 | St. Jude Medical, Cardiology Division, Inc. | Valve holder with leaflet protection |
US10588746B2 (en) * | 2013-03-08 | 2020-03-17 | Carnegie Mellon University | Expandable implantable conduit |
US10271949B2 (en) | 2013-03-12 | 2019-04-30 | St. Jude Medical, Cardiology Division, Inc. | Paravalvular leak occlusion device for self-expanding heart valves |
US9636222B2 (en) | 2013-03-12 | 2017-05-02 | St. Jude Medical, Cardiology Division, Inc. | Paravalvular leak protection |
US10314698B2 (en) | 2013-03-12 | 2019-06-11 | St. Jude Medical, Cardiology Division, Inc. | Thermally-activated biocompatible foam occlusion device for self-expanding heart valves |
EP2967849A4 (en) | 2013-03-12 | 2017-01-18 | St. Jude Medical, Cardiology Division, Inc. | Self-actuating sealing portions for paravalvular leak protection |
US9398951B2 (en) | 2013-03-12 | 2016-07-26 | St. Jude Medical, Cardiology Division, Inc. | Self-actuating sealing portions for paravalvular leak protection |
US9339274B2 (en) | 2013-03-12 | 2016-05-17 | St. Jude Medical, Cardiology Division, Inc. | Paravalvular leak occlusion device for self-expanding heart valves |
ES2860600T3 (en) | 2013-03-13 | 2021-10-05 | Jenesis Surgical Llc | Articulated commissure valve endoprosthesis |
US9326856B2 (en) | 2013-03-14 | 2016-05-03 | St. Jude Medical, Cardiology Division, Inc. | Cuff configurations for prosthetic heart valve |
US9131982B2 (en) | 2013-03-14 | 2015-09-15 | St. Jude Medical, Cardiology Division, Inc. | Mediguide-enabled renal denervation system for ensuring wall contact and mapping lesion locations |
GB201307965D0 (en) | 2013-05-02 | 2013-06-12 | Cook Medical Technologies Llc | Vascular plug |
US11076952B2 (en) | 2013-06-14 | 2021-08-03 | The Regents Of The University Of California | Collapsible atrioventricular valve prosthesis |
US9968445B2 (en) * | 2013-06-14 | 2018-05-15 | The Regents Of The University Of California | Transcatheter mitral valve |
US10321991B2 (en) | 2013-06-19 | 2019-06-18 | St. Jude Medical, Cardiology Division, Inc. | Collapsible valve having paravalvular leak protection |
US9668856B2 (en) | 2013-06-26 | 2017-06-06 | St. Jude Medical, Cardiology Division, Inc. | Puckering seal for reduced paravalvular leakage |
US8870948B1 (en) | 2013-07-17 | 2014-10-28 | Cephea Valve Technologies, Inc. | System and method for cardiac valve repair and replacement |
US9681876B2 (en) | 2013-07-31 | 2017-06-20 | EMBA Medical Limited | Methods and devices for endovascular embolization |
US10010328B2 (en) | 2013-07-31 | 2018-07-03 | NeuVT Limited | Endovascular occlusion device with hemodynamically enhanced sealing and anchoring |
US9549748B2 (en) | 2013-08-01 | 2017-01-24 | Cook Medical Technologies Llc | Methods of locating and treating tissue in a wall defining a bodily passage |
CN105451686B (en) | 2013-08-14 | 2018-03-20 | 索林集团意大利有限责任公司 | Apparatus and method for chordae tendineae displacement |
USD730520S1 (en) | 2013-09-04 | 2015-05-26 | St. Jude Medical, Cardiology Division, Inc. | Stent with commissure attachments |
USD730521S1 (en) | 2013-09-04 | 2015-05-26 | St. Jude Medical, Cardiology Division, Inc. | Stent with commissure attachments |
US9867611B2 (en) | 2013-09-05 | 2018-01-16 | St. Jude Medical, Cardiology Division, Inc. | Anchoring studs for transcatheter valve implantation |
US10117742B2 (en) | 2013-09-12 | 2018-11-06 | St. Jude Medical, Cardiology Division, Inc. | Stent designs for prosthetic heart valves |
GB201316349D0 (en) | 2013-09-13 | 2013-10-30 | Ucl Business Plc | Vascular implant |
US9839511B2 (en) | 2013-10-05 | 2017-12-12 | Sino Medical Sciences Technology Inc. | Device and method for mitral valve regurgitation treatment |
US9393111B2 (en) | 2014-01-15 | 2016-07-19 | Sino Medical Sciences Technology Inc. | Device and method for mitral valve regurgitation treatment |
GB2523291B (en) * | 2013-10-16 | 2016-02-24 | Cook Medical Technologies Llc | Vascular occluder with crossing frame elements |
US9700409B2 (en) | 2013-11-06 | 2017-07-11 | St. Jude Medical, Cardiology Division, Inc. | Reduced profile prosthetic heart valve |
EP2870946B1 (en) * | 2013-11-06 | 2018-10-31 | 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 |
CN116158889A (en) | 2013-11-11 | 2023-05-26 | 爱德华兹生命科学卡迪尔克有限责任公司 | System and method for manufacturing a stent frame |
US9549818B2 (en) | 2013-11-12 | 2017-01-24 | St. Jude Medical, Cardiology Division, Inc. | Pneumatically power-assisted tavi delivery system |
EP3071149B1 (en) | 2013-11-19 | 2022-06-01 | St. Jude Medical, Cardiology Division, Inc. | Sealing structures for paravalvular leak protection |
US10314693B2 (en) | 2013-11-27 | 2019-06-11 | St. Jude Medical, Cardiology Division, Inc. | Cuff stitching reinforcement |
EP3583921A1 (en) | 2013-12-19 | 2019-12-25 | St. Jude Medical, Cardiology Division, Inc. | Leaflet-cuff attachments for prosthetic heart valve |
US10350098B2 (en) | 2013-12-20 | 2019-07-16 | Volcano Corporation | Devices and methods for controlled endoluminal filter deployment |
US9820852B2 (en) | 2014-01-24 | 2017-11-21 | St. Jude Medical, Cardiology Division, Inc. | Stationary intra-annular halo designs for paravalvular leak (PVL) reduction—active channel filling cuff designs |
EP2898920B1 (en) | 2014-01-24 | 2018-06-06 | Cook Medical Technologies LLC | Articulating balloon catheter |
US20150209141A1 (en) | 2014-01-24 | 2015-07-30 | St. Jude Medical, Cardiology Division, Inc. | Stationary intra-annular halo designs for paravalvular leak (pvl) reduction-passive channel filling cuff designs |
US10292711B2 (en) | 2014-02-07 | 2019-05-21 | St. Jude Medical, Cardiology Division, Inc. | Mitral valve treatment device having left atrial appendage closure |
EP2904967A1 (en) | 2014-02-07 | 2015-08-12 | St. Jude Medical, Cardiology Division, Inc. | System and method for assessing dimensions and eccentricity of valve annulus for trans-catheter valve implantation |
EP3107496B1 (en) | 2014-02-18 | 2018-07-04 | St. Jude Medical, Cardiology Division, Inc. | Bowed runners for paravalvular leak protection |
US9937323B2 (en) | 2014-02-28 | 2018-04-10 | Cook Medical Technologies Llc | Deflectable catheters, systems, and methods for the visualization and treatment of bodily passages |
ES2711663T3 (en) * | 2014-03-18 | 2019-05-06 | Nvt Ag | Cardiac valve implant |
EP2921140A1 (en) | 2014-03-18 | 2015-09-23 | St. Jude Medical, Cardiology Division, Inc. | Percutaneous valve anchoring for a prosthetic aortic valve |
US10085834B2 (en) | 2014-03-18 | 2018-10-02 | St. Jude Medical, Cardiology Divsion, Inc. | Mitral valve replacement toggle cell securement |
WO2015143103A1 (en) | 2014-03-21 | 2015-09-24 | St. Jude Medical, Cardiology Division, Inc. | Leaflet abrasion mitigation |
JP6526043B2 (en) | 2014-03-26 | 2019-06-05 | セント・ジュード・メディカル,カーディオロジー・ディヴィジョン,インコーポレイテッド | Transcatheter mitral valve stent frame |
EP3125826B1 (en) | 2014-03-31 | 2020-10-07 | St. Jude Medical, Cardiology Division, Inc. | Paravalvular sealing via extended cuff mechanisms |
US10226332B2 (en) | 2014-04-14 | 2019-03-12 | St. Jude Medical, Cardiology Division, Inc. | Leaflet abrasion mitigation in prosthetic heart valves |
US10154904B2 (en) | 2014-04-28 | 2018-12-18 | Edwards Lifesciences Corporation | Intravascular introducer devices |
US20170189175A1 (en) | 2014-05-07 | 2017-07-06 | Baylor College Of Medicine | Artificial, flexible valves and methods of fabricating and serially expanding the same |
US10195025B2 (en) | 2014-05-12 | 2019-02-05 | Edwards Lifesciences Corporation | Prosthetic heart valve |
ES2795358T3 (en) | 2014-05-16 | 2020-11-23 | St Jude Medical Cardiology Div Inc | Subannular sealing for paravalvular leak protection |
EP3257473A1 (en) | 2014-05-16 | 2017-12-20 | St. Jude Medical, Cardiology Division, Inc. | Stent assembly for use in prosthetic heart valves |
EP3142604B1 (en) | 2014-05-16 | 2024-01-10 | St. Jude Medical, Cardiology Division, Inc. | Transcatheter valve with paravalvular leak sealing ring |
EP3145450B1 (en) | 2014-05-22 | 2019-07-17 | St. Jude Medical, Cardiology Division, Inc. | Stents with anchoring sections |
US9808230B2 (en) | 2014-06-06 | 2017-11-07 | W. L. Gore & Associates, Inc. | Sealing device and delivery system |
EP2954875B1 (en) | 2014-06-10 | 2017-11-15 | St. Jude Medical, Cardiology Division, Inc. | Stent cell bridge for cuff attachment |
US10195398B2 (en) | 2014-08-13 | 2019-02-05 | Cook Medical Technologies Llc | Tension member seal and securing mechanism for medical devices |
US9808201B2 (en) | 2014-08-18 | 2017-11-07 | St. Jude Medical, Cardiology Division, Inc. | Sensors for prosthetic heart devices |
WO2016028585A1 (en) | 2014-08-18 | 2016-02-25 | St. Jude Medical, Cardiology Division, Inc. | Sensors for prosthetic heart devices |
EP3182927A1 (en) | 2014-08-18 | 2017-06-28 | St. Jude Medical, Cardiology Division, Inc. | Prosthetic heart devices having diagnostic capabilities |
US10143544B2 (en) | 2014-08-29 | 2018-12-04 | Cook Medical Technologies Llc | Low profile intraluminal medical devices |
US10010399B2 (en) | 2014-08-29 | 2018-07-03 | Cook Medical Technologies Llc | Low profile intraluminal filters |
US20160095701A1 (en) * | 2014-10-07 | 2016-04-07 | St. Jude Medical, Cardiology Division, Inc. | Bi-Leaflet Mitral Valve Design |
US9492273B2 (en) | 2014-12-09 | 2016-11-15 | Cephea Valve Technologies, Inc. | Replacement cardiac valves and methods of use and manufacture |
EP4344676A1 (en) | 2014-12-14 | 2024-04-03 | Trisol Medical Ltd. | Prosthetic valve and deployment system |
US10314699B2 (en) | 2015-03-13 | 2019-06-11 | St. Jude Medical, Cardiology Division, Inc. | Recapturable valve-graft combination and related methods |
EP3273912A1 (en) | 2015-03-23 | 2018-01-31 | St. Jude Medical, Cardiology Division, Inc. | Heart valve repair |
US9962260B2 (en) | 2015-03-24 | 2018-05-08 | St. Jude Medical, Cardiology Division, Inc. | Prosthetic mitral valve |
US10070954B2 (en) | 2015-03-24 | 2018-09-11 | St. Jude Medical, Cardiology Division, Inc. | Mitral heart valve replacement |
US10716672B2 (en) | 2015-04-07 | 2020-07-21 | St. Jude Medical, Cardiology Division, Inc. | System and method for intraprocedural assessment of geometry and compliance of valve annulus for trans-catheter valve implantation |
EP3294220B1 (en) | 2015-05-14 | 2023-12-06 | Cephea Valve Technologies, Inc. | Cardiac valve delivery devices and systems |
WO2018136959A1 (en) | 2017-01-23 | 2018-07-26 | Cephea Valve Technologies, Inc. | Replacement mitral valves |
AU2016262564B2 (en) | 2015-05-14 | 2020-11-05 | Cephea Valve Technologies, Inc. | Replacement mitral valves |
EP3307207A1 (en) | 2015-06-12 | 2018-04-18 | St. Jude Medical, Cardiology Division, Inc. | Heart valve repair and replacement |
US9974650B2 (en) | 2015-07-14 | 2018-05-22 | Edwards Lifesciences Corporation | Prosthetic heart valve |
JP6600068B2 (en) | 2015-07-16 | 2019-10-30 | セント・ジュード・メディカル,カーディオロジー・ディヴィジョン,インコーポレイテッド | Non-sutured prosthetic heart valve |
US10368983B2 (en) | 2015-08-12 | 2019-08-06 | St. Jude Medical, Cardiology Division, Inc. | Collapsible heart valve including stents with tapered struts |
US10779940B2 (en) | 2015-09-03 | 2020-09-22 | Boston Scientific Scimed, Inc. | Medical device handle |
WO2017062762A2 (en) | 2015-10-07 | 2017-04-13 | Sigmon John C | Methods, medical devices and kits for modifying the luminal profile of a body vessel |
US10179043B2 (en) | 2016-02-12 | 2019-01-15 | Edwards Lifesciences Corporation | Prosthetic heart valve having multi-level sealing member |
WO2017151900A1 (en) | 2016-03-02 | 2017-09-08 | Peca Labs, Inc. | Expandable implantable conduit |
US20190076231A1 (en) | 2016-03-10 | 2019-03-14 | Keystone Heart Ltd. | Intra-Aortic Device |
USD802766S1 (en) | 2016-05-13 | 2017-11-14 | St. Jude Medical, Cardiology Division, Inc. | Surgical stent |
USD802764S1 (en) | 2016-05-13 | 2017-11-14 | St. Jude Medical, Cardiology Division, Inc. | Surgical stent |
USD802765S1 (en) | 2016-05-13 | 2017-11-14 | St. Jude Medical, Cardiology Division, Inc. | Surgical stent |
US10321994B2 (en) | 2016-05-13 | 2019-06-18 | St. Jude Medical, Cardiology Division, Inc. | Heart valve with stent having varying cell densities |
US10245136B2 (en) | 2016-05-13 | 2019-04-02 | Boston Scientific Scimed Inc. | Containment vessel with implant sheathing guide |
WO2017218877A1 (en) | 2016-06-17 | 2017-12-21 | Cephea Valve Technologies, Inc. | Cardiac valve delivery devices and systems |
ES2902516T3 (en) | 2016-08-26 | 2022-03-28 | St Jude Medical Cardiology Div Inc | Prosthetic heart valve with paravalvular leak mitigation features |
EP3512466B1 (en) | 2016-09-15 | 2020-07-29 | St. Jude Medical, Cardiology Division, Inc. | Prosthetic heart valve with paravalvular leak mitigation features |
EP3522830A4 (en) | 2016-10-10 | 2020-06-17 | Peca Labs, Inc. | Transcatheter stent and valve assembly |
EP3531977A1 (en) | 2016-10-28 | 2019-09-04 | St. Jude Medical, Cardiology Division, Inc. | Prosthetic mitral valve |
US10631986B2 (en) | 2016-12-02 | 2020-04-28 | St. Jude Medical, Cardiology Division, Inc. | Transcatheter delivery system with transverse wheel actuation |
EP3547965A1 (en) | 2016-12-02 | 2019-10-09 | St. Jude Medical, Cardiology Division, Inc. | Transcatheter delivery system with two modes of actuation |
US10813749B2 (en) | 2016-12-20 | 2020-10-27 | Edwards Lifesciences Corporation | Docking device made with 3D woven fabric |
EP4209196A1 (en) | 2017-01-23 | 2023-07-12 | Cephea Valve Technologies, Inc. | Replacement mitral valves |
US11376112B2 (en) | 2017-01-31 | 2022-07-05 | W. L. Gore & Associates, Inc. | Pre-strained stent elements |
WO2018160790A1 (en) | 2017-03-03 | 2018-09-07 | St. Jude Medical, Cardiology Division, Inc. | Transcatheter mitral valve design |
USD875935S1 (en) | 2017-05-15 | 2020-02-18 | St. Jude Medical, Cardiology Division, Inc. | Stent having tapered struts |
USD875250S1 (en) | 2017-05-15 | 2020-02-11 | St. Jude Medical, Cardiology Division, Inc. | Stent having tapered aortic struts |
USD889653S1 (en) | 2017-05-15 | 2020-07-07 | St. Jude Medical, Cardiology Division, Inc. | Stent having tapered struts |
EP3624739A1 (en) | 2017-05-15 | 2020-03-25 | St. Jude Medical, Cardiology Division, Inc. | Transcatheter delivery system with wheel actuation |
EP3634315A4 (en) | 2017-05-31 | 2020-04-22 | Edwards Lifesciences Corporation | Sealing member for prosthetic heart valve |
US11382751B2 (en) | 2017-10-24 | 2022-07-12 | St. Jude Medical, Cardiology Division, Inc. | Self-expandable filler for mitigating paravalvular leak |
EP3476365A1 (en) * | 2017-10-27 | 2019-05-01 | Keystone Heart Ltd. | A dome shaped filtering device and method of manufacturing the same |
US10959864B2 (en) | 2018-01-11 | 2021-03-30 | Cook Medical Technologies Llc | Barbed wire stent |
US11813413B2 (en) | 2018-03-27 | 2023-11-14 | St. Jude Medical, Cardiology Division, Inc. | Radiopaque outer cuff for transcatheter valve |
US11234812B2 (en) | 2018-04-18 | 2022-02-01 | St. Jude Medical, Cardiology Division, Inc. | Methods for surgical valve expansion |
EP3796868A4 (en) * | 2018-05-22 | 2022-04-06 | Filterlex Medical Ltd. | Intra-aortic embolic protection filter device |
EP3852679A1 (en) | 2018-09-20 | 2021-07-28 | St. Jude Medical, Cardiology Division, Inc. | Attachment of leaflets to prosthetic heart valve |
US11364117B2 (en) | 2018-10-15 | 2022-06-21 | St. Jude Medical, Cardiology Division, Inc. | Braid connections for prosthetic heart valves |
EP3852683A1 (en) * | 2018-11-01 | 2021-07-28 | Edwards Lifesciences Corporation | Transcatheter pulmonic regenerative valve |
WO2020123267A1 (en) | 2018-12-10 | 2020-06-18 | St. Jude Medical, Cardiology Division, Inc. | Prosthetic tricuspid valve replacement design |
US11925570B2 (en) | 2018-12-19 | 2024-03-12 | Boston Scientific Scimed, Inc. | Stent including anti-migration capabilities |
EP3902503A1 (en) | 2018-12-26 | 2021-11-03 | St. Jude Medical, Cardiology Division, Inc. | Elevated outer cuff for reducing paravalvular leakage and increasing stent fatigue life |
JP2022531433A (en) * | 2019-05-03 | 2022-07-06 | リクロス・カーディオ・インコーポレイテッド | Passable bulkhead blockage device |
EP4003230A1 (en) | 2019-07-31 | 2022-06-01 | St. Jude Medical, Cardiology Division, Inc. | Alternate stent caf design for tavr |
CN111312891A (en) * | 2020-02-24 | 2020-06-19 | 西安交通大学 | Flexible GMR magnetic field sensor and preparation method thereof |
US11938022B2 (en) * | 2020-06-26 | 2024-03-26 | Highlife Sas | Transcatheter valve prosthesis and method for implanting the same |
DE102020122386A1 (en) * | 2020-08-27 | 2022-03-03 | MEDIRA GmbH | Prosthetic valve device for treating mitral valve regurgitation |
CN115462934B (en) * | 2022-10-08 | 2023-07-14 | 浙江归创医疗科技有限公司 | Detachable venous valve |
Citations (65)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4218783A (en) * | 1977-09-22 | 1980-08-26 | Dr. E. Fresenius, Chem.-Pharm. Industrie KG | Prosthetic closure element for the replacement of the mitral and tricuspid valve in the human heart |
US4580568A (en) * | 1984-10-01 | 1986-04-08 | Cook, Incorporated | Percutaneous endovascular stent and method for insertion thereof |
US4902508A (en) * | 1988-07-11 | 1990-02-20 | Purdue Research Foundation | Tissue graft composition |
US4994077A (en) * | 1989-04-21 | 1991-02-19 | Dobben Richard L | Artificial heart valve for implantation in a blood vessel |
US5035706A (en) * | 1989-10-17 | 1991-07-30 | Cook Incorporated | Percutaneous stent and method for retrieval thereof |
US5108420A (en) * | 1991-02-01 | 1992-04-28 | Temple University | Aperture occlusion device |
US5116564A (en) * | 1988-10-11 | 1992-05-26 | Josef Jansen | Method of producing a closing member having flexible closing elements, especially a heart valve |
US5123919A (en) * | 1991-11-21 | 1992-06-23 | Carbomedics, Inc. | Combined prosthetic aortic heart valve and vascular graft |
US5147389A (en) * | 1986-07-17 | 1992-09-15 | Vaso Products Australia Pty Limited | Correction of incompetent venous valves |
US5171259A (en) * | 1990-04-02 | 1992-12-15 | Kanji Inoue | Device for nonoperatively occluding a defect |
US5335341A (en) * | 1990-12-20 | 1994-08-02 | International Business Machines Corporation | Dump analysis system and method in data processing systems |
US5334217A (en) * | 1992-01-21 | 1994-08-02 | Regents Of The University Of Minnesota | Septal defect closure device |
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 |
US5451235A (en) * | 1991-11-05 | 1995-09-19 | C.R. Bard, Inc. | Occluder and method for repair of cardiac and vascular defects |
US5480424A (en) * | 1993-11-01 | 1996-01-02 | Cox; James L. | Heart valve replacement using flexible tubes |
US5489297A (en) * | 1992-01-27 | 1996-02-06 | Duran; Carlos M. G. | Bioprosthetic heart valve with absorbable stent |
US5500014A (en) * | 1989-05-31 | 1996-03-19 | Baxter International Inc. | Biological valvular prothesis |
US5607465A (en) * | 1993-12-14 | 1997-03-04 | Camilli; Sante | Percutaneous implantable valve for the use in blood vessels |
US5630829A (en) * | 1994-12-09 | 1997-05-20 | Intervascular, Inc. | High hoop strength intraluminal stent |
US5643317A (en) * | 1992-11-25 | 1997-07-01 | William Cook Europe S.A. | Closure prosthesis for transcatheter placement |
US5643312A (en) * | 1994-02-25 | 1997-07-01 | Fischell Robert | Stent having a multiplicity of closed circular structures |
US5709707A (en) * | 1995-10-30 | 1998-01-20 | Children's Medical Center Corporation | Self-centering umbrella-type septal closure device |
US5713950A (en) * | 1993-11-01 | 1998-02-03 | Cox; James L. | Method of replacing heart valves using flexible tubes |
US5728152A (en) * | 1995-06-07 | 1998-03-17 | St. Jude Medical, Inc. | Bioresorbable heart valve support |
US5733325A (en) * | 1993-11-04 | 1998-03-31 | C. R. Bard, Inc. | Non-migrating vascular prosthesis and minimally invasive placement system |
US5746766A (en) * | 1995-05-09 | 1998-05-05 | Edoga; John K. | Surgical stent |
US5810847A (en) * | 1994-12-30 | 1998-09-22 | Vnus Medical Technologies, Inc. | Method and apparatus for minimally invasive treatment of chronic venous insufficiency |
US5824061A (en) * | 1989-05-31 | 1998-10-20 | Baxter International Inc. | Vascular and venous valve implant prostheses |
US5840081A (en) * | 1990-05-18 | 1998-11-24 | Andersen; Henning Rud | System and method for implanting cardiac valves |
US5855597A (en) * | 1997-05-07 | 1999-01-05 | Iowa-India Investments Co. Limited | Stent valve and stent graft for percutaneous surgery |
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 |
US5861003A (en) * | 1996-10-23 | 1999-01-19 | The Cleveland Clinic Foundation | Apparatus and method for occluding a defect or aperture within body surface |
US5876434A (en) * | 1997-07-13 | 1999-03-02 | Litana Ltd. | Implantable medical devices of shape memory alloy |
US5879382A (en) * | 1989-08-24 | 1999-03-09 | Boneau; Michael D. | Endovascular support device and method |
US5888201A (en) * | 1996-02-08 | 1999-03-30 | Schneider (Usa) Inc | Titanium alloy self-expanding stent |
US5907893A (en) * | 1996-01-30 | 1999-06-01 | Medtronic, Inc. | Methods for the manufacture of radially expansible stents |
US5957949A (en) * | 1997-05-01 | 1999-09-28 | World Medical Manufacturing Corp. | Percutaneous placement valve stent |
US6010530A (en) * | 1995-06-07 | 2000-01-04 | Boston Scientific Technology, Inc. | Self-expanding endoluminal prosthesis |
US6027525A (en) * | 1996-05-23 | 2000-02-22 | Samsung Electronics., Ltd. | Flexible self-expandable stent and method for making the same |
US6126686A (en) * | 1996-12-10 | 2000-10-03 | Purdue Research Foundation | Artificial vascular valves |
US6174328B1 (en) * | 1992-02-21 | 2001-01-16 | Boston Scientific Technology, Inc. | Intraluminal stent and graft |
US6183495B1 (en) * | 1997-05-05 | 2001-02-06 | Micro Therapeutics, Inc. | Wire frame partial flow obstruction device for aneurysm treatment |
US6200336B1 (en) * | 1998-06-02 | 2001-03-13 | Cook Incorporated | Multiple-sided intraluminal medical device |
US6245102B1 (en) * | 1997-05-07 | 2001-06-12 | Iowa-India Investments Company Ltd. | Stent, stent graft and stent valve |
US6245103B1 (en) * | 1997-08-01 | 2001-06-12 | Schneider (Usa) Inc | Bioabsorbable self-expanding stent |
US6254636B1 (en) * | 1998-06-26 | 2001-07-03 | St. Jude Medical, Inc. | Single suture biological tissue aortic stentless valve |
US6280467B1 (en) * | 1998-02-26 | 2001-08-28 | World Medical Manufacturing Corporation | Delivery system for deployment and endovascular assembly of a multi-stage stented graft |
US6287334B1 (en) * | 1996-12-18 | 2001-09-11 | Venpro Corporation | Device for regulating the flow of blood through the blood system |
US6299637B1 (en) * | 1999-08-20 | 2001-10-09 | Samuel M. Shaolian | Transluminally implantable venous valve |
US6312474B1 (en) * | 1999-09-15 | 2001-11-06 | Bio-Vascular, Inc. | Resorbable implant materials |
US20010039450A1 (en) * | 1999-06-02 | 2001-11-08 | Dusan Pavcnik | Implantable vascular device |
US20020099439A1 (en) * | 2000-09-29 | 2002-07-25 | Schwartz Robert S. | Venous valvuloplasty device and method |
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 |
US6503272B2 (en) * | 2001-03-21 | 2003-01-07 | Cordis Corporation | Stent-based venous valves |
US20030023303A1 (en) * | 1999-11-19 | 2003-01-30 | Palmaz Julio C. | Valvular prostheses having metal or pseudometallic construction and methods of manufacture |
US20030130726A1 (en) * | 1999-09-10 | 2003-07-10 | Thorpe Patricia E. | Combination valve and stent for treating vascular reflux |
US20030191525A1 (en) * | 2002-04-03 | 2003-10-09 | Thornton Sally C. | Artifical valve |
US20030208261A1 (en) * | 2000-03-03 | 2003-11-06 | Thorpe Patricia E. | Bulbous valve and stent for treating vascular reflux |
US6652582B1 (en) * | 1997-08-01 | 2003-11-25 | Boston Scientific Scimed, Inc. | Bioabsorbable endoprosthesis having porosity for by-product collection |
US20030225447A1 (en) * | 2002-05-10 | 2003-12-04 | Majercak David Christopher | Method of making a medical device having a thin wall tubular membrane over a structural frame |
US6676698B2 (en) * | 2000-06-26 | 2004-01-13 | Rex Medicol, L.P. | Vascular device with valve for approximating vessel wall |
US20040034408A1 (en) * | 2002-05-10 | 2004-02-19 | Majercak David Christopher | Method of placing a tubular membrane on a structural frame |
US20040093060A1 (en) * | 1999-11-17 | 2004-05-13 | Jacques Seguin | Prosthetic valve for transluminal delivery |
Family Cites Families (34)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4291420A (en) * | 1973-11-09 | 1981-09-29 | Medac Gesellschaft Fur Klinische Spezialpraparate Mbh | Artificial heart valve |
DK229077A (en) * | 1977-05-25 | 1978-11-26 | Biocoating Aps | HEARTBALL PROSTHET AND PROCEDURE FOR MANUFACTURING IT |
US4222126A (en) * | 1978-12-14 | 1980-09-16 | The United States Of America As Represented By The Secretary Of The Department Of Health, Education & Welfare | Unitized three leaflet heart valve |
US5035708A (en) * | 1985-06-06 | 1991-07-30 | Thomas Jefferson University | Endothelial cell procurement and deposition kit |
US4733665C2 (en) | 1985-11-07 | 2002-01-29 | Expandable Grafts Partnership | Expandable intraluminal graft and method and apparatus for implanting an expandable intraluminal graft |
JPS63503239A (en) * | 1986-01-18 | 1988-11-24 | コルデコ ソシエテ アノニム | Method for accumulating and restoring cold air and equipment for carrying out the method |
US5156621A (en) * | 1988-03-22 | 1992-10-20 | Navia Jose A | Stentless bioprosthetic cardiac valve |
DE9117152U1 (en) | 1990-10-09 | 1996-07-11 | Cook Inc | Stent |
US5156620A (en) * | 1991-02-04 | 1992-10-20 | Pigott John P | Intraluminal graft/stent and balloon catheter for insertion thereof |
US5281422A (en) * | 1991-09-24 | 1994-01-25 | Purdue Research Foundation | Graft for promoting autogenous tissue growth |
DE69332644T2 (en) | 1993-08-20 | 2003-09-25 | Kanji Inoue | IMPLANT AND METHOD FOR FOLDING IT UP |
GB9324201D0 (en) | 1993-11-24 | 1994-01-12 | London Health Ass | Stentless heart valve surgical support device |
DK171019B1 (en) | 1993-12-02 | 1996-04-22 | Maersk Container Ind As | Refrigerator and gable frame |
DE69527141T2 (en) | 1994-04-29 | 2002-11-07 | Scimed Life Systems Inc | STENT WITH COLLAGEN |
JP3647456B2 (en) | 1994-04-29 | 2005-05-11 | ボストン・サイエンティフィック・コーポレーション | Medical artificial stent and method for producing the same |
DE4424242A1 (en) | 1994-07-09 | 1996-01-11 | Ernst Peter Prof Dr M Strecker | Endoprosthesis implantable percutaneously in a patient's body |
AU3783195A (en) | 1994-11-15 | 1996-05-23 | Advanced Cardiovascular Systems Inc. | Intraluminal stent for attaching a graft |
RU2108070C1 (en) | 1996-07-09 | 1998-04-10 | Борис Петрович Кручинин | Microsurgical fastening device and manipulation pusher for its mounting |
FR2750853B1 (en) | 1996-07-10 | 1998-12-18 | Braun Celsa Sa | MEDICAL PROSTHESIS, IN PARTICULAR FOR ANEVRISMS, WITH PERFECTIONED CONNECTION BETWEEN ITS SHEATH AND ITS STRUCTURE |
US6494904B1 (en) * | 1996-12-27 | 2002-12-17 | Ramus Medical Technologies | Method and apparatus for forming vascular prostheses |
EP0850607A1 (en) | 1996-12-31 | 1998-07-01 | Cordis Corporation | Valve prosthesis for implantation in body channels |
US5925063A (en) | 1997-09-26 | 1999-07-20 | Khosravi; Farhad | Coiled sheet valve, filter or occlusive device and methods of use |
US6200338B1 (en) * | 1998-12-31 | 2001-03-13 | Ethicon, Inc. | Enhanced radiopacity of peripheral and central catheter tubing |
US6425916B1 (en) * | 1999-02-10 | 2002-07-30 | Michi E. Garrison | Methods and devices for implanting cardiac valves |
US6110201A (en) * | 1999-02-18 | 2000-08-29 | Venpro | Bifurcated biological pulmonary valved conduit |
WO2000064381A2 (en) * | 1999-04-28 | 2000-11-02 | St. Jude Medical, Inc. | Heart valve prostheses |
CA2297273A1 (en) * | 2000-01-26 | 2001-07-26 | Michael D. Perelgut | 3 dimensional imaging of hard structure without the use of ionizing radiation |
ES2286097T7 (en) | 2000-01-31 | 2009-11-05 | Cook Biotech, Inc | ENDOPROTESIS VALVES. |
US6585761B2 (en) * | 2001-03-01 | 2003-07-01 | Syde A. Taheri | Prosthetic vein valve and method |
AU2002254758A1 (en) | 2001-04-30 | 2002-11-11 | Francisco J. Osse | Replacement venous valve |
US7547322B2 (en) * | 2001-07-19 | 2009-06-16 | The Cleveland Clinic Foundation | Prosthetic valve and method for making same |
AU2003217603A1 (en) | 2002-02-20 | 2003-09-09 | Francisco J. Osse | Venous bi-valve |
US6716241B2 (en) * | 2002-03-05 | 2004-04-06 | John G. Wilder | Venous valve and graft combination |
US7163556B2 (en) * | 2002-03-21 | 2007-01-16 | Providence Health System - Oregon | Bioprosthesis and method for suturelessly making same |
-
2001
- 2001-02-05 US US09/777,091 patent/US7452371B2/en not_active Expired - Lifetime
-
2003
- 2003-11-25 US US10/721,582 patent/US7597710B2/en not_active Expired - Lifetime
-
2004
- 2004-08-03 US US10/910,490 patent/US20050143807A1/en not_active Abandoned
-
2005
- 2005-06-22 US US11/165,600 patent/US7520894B2/en not_active Expired - Lifetime
-
2008
- 2008-10-27 US US12/258,757 patent/US8613763B2/en not_active Expired - Fee Related
-
2009
- 2009-02-26 US US12/393,819 patent/US8444687B2/en not_active Expired - Lifetime
Patent Citations (79)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US4218783A (en) * | 1977-09-22 | 1980-08-26 | Dr. E. Fresenius, Chem.-Pharm. Industrie KG | Prosthetic closure element for the replacement of the mitral and tricuspid valve in the human heart |
US4580568A (en) * | 1984-10-01 | 1986-04-08 | Cook, Incorporated | Percutaneous endovascular stent and method for insertion thereof |
US5147389A (en) * | 1986-07-17 | 1992-09-15 | Vaso Products Australia Pty Limited | Correction of incompetent venous valves |
US4902508A (en) * | 1988-07-11 | 1990-02-20 | Purdue Research Foundation | Tissue graft composition |
US5116564A (en) * | 1988-10-11 | 1992-05-26 | Josef Jansen | Method of producing a closing member having flexible closing elements, especially a heart valve |
US4994077A (en) * | 1989-04-21 | 1991-02-19 | Dobben Richard L | Artificial heart valve for implantation in a blood vessel |
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 |
US5879382A (en) * | 1989-08-24 | 1999-03-09 | Boneau; Michael D. | Endovascular support device and method |
US5035706A (en) * | 1989-10-17 | 1991-07-30 | Cook Incorporated | Percutaneous stent and method for retrieval thereof |
US5171259A (en) * | 1990-04-02 | 1992-12-15 | Kanji Inoue | Device for nonoperatively occluding a defect |
US6582462B1 (en) * | 1990-05-18 | 2003-06-24 | Heartport, Inc. | Valve prosthesis for implantation in the body and a catheter for implanting such valve prosthesis |
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 |
US20030036795A1 (en) * | 1990-05-18 | 2003-02-20 | Andersen Henning Rud | Valve prosthesis for implantation in the body and a catheter for implanting such valve prosthesis |
US6168614B1 (en) * | 1990-05-18 | 2001-01-02 | Heartport, Inc. | Valve prosthesis for implantation in the body |
US5335341A (en) * | 1990-12-20 | 1994-08-02 | International Business Machines Corporation | Dump analysis system and method in data processing systems |
US5108420A (en) * | 1991-02-01 | 1992-04-28 | Temple University | Aperture occlusion device |
US5358518A (en) * | 1991-06-25 | 1994-10-25 | Sante Camilli | Artificial venous valve |
US5451235A (en) * | 1991-11-05 | 1995-09-19 | C.R. Bard, Inc. | Occluder and method for repair of cardiac and vascular defects |
US5123919A (en) * | 1991-11-21 | 1992-06-23 | Carbomedics, Inc. | Combined prosthetic aortic heart valve and vascular graft |
US6077281A (en) * | 1992-01-21 | 2000-06-20 | Regents Of The University Of Minnesota | Septal defect closure device |
US5334217A (en) * | 1992-01-21 | 1994-08-02 | Regents Of The University Of Minnesota | Septal defect closure device |
US5489297A (en) * | 1992-01-27 | 1996-02-06 | Duran; Carlos M. G. | Bioprosthetic heart valve with absorbable stent |
US6174328B1 (en) * | 1992-02-21 | 2001-01-16 | Boston Scientific Technology, Inc. | Intraluminal stent and graft |
US5643317A (en) * | 1992-11-25 | 1997-07-01 | William Cook Europe S.A. | Closure prosthesis for transcatheter placement |
US5713950A (en) * | 1993-11-01 | 1998-02-03 | Cox; James L. | Method of replacing heart valves using flexible tubes |
US5480424A (en) * | 1993-11-01 | 1996-01-02 | Cox; James L. | Heart valve replacement using flexible tubes |
US5824063A (en) * | 1993-11-01 | 1998-10-20 | Cox; James L. | Method of replacing atrioventricular heart valves using flexible tubes |
US5733325A (en) * | 1993-11-04 | 1998-03-31 | C. R. Bard, Inc. | Non-migrating vascular prosthesis and minimally invasive placement system |
US5607465A (en) * | 1993-12-14 | 1997-03-04 | Camilli; Sante | Percutaneous implantable valve for the use in blood vessels |
US5643312A (en) * | 1994-02-25 | 1997-07-01 | Fischell Robert | Stent having a multiplicity of closed circular structures |
US5630829A (en) * | 1994-12-09 | 1997-05-20 | Intervascular, Inc. | High hoop strength intraluminal stent |
US5810847A (en) * | 1994-12-30 | 1998-09-22 | Vnus Medical Technologies, Inc. | Method and apparatus for minimally invasive treatment of chronic venous insufficiency |
US5746766A (en) * | 1995-05-09 | 1998-05-05 | Edoga; John K. | Surgical stent |
US5728152A (en) * | 1995-06-07 | 1998-03-17 | St. Jude Medical, Inc. | Bioresorbable heart valve support |
US6010530A (en) * | 1995-06-07 | 2000-01-04 | Boston Scientific Technology, Inc. | Self-expanding endoluminal prosthesis |
US5709707A (en) * | 1995-10-30 | 1998-01-20 | Children's Medical Center Corporation | Self-centering umbrella-type septal closure device |
US5907893A (en) * | 1996-01-30 | 1999-06-01 | Medtronic, Inc. | Methods for the manufacture of radially expansible stents |
US6327772B1 (en) * | 1996-01-30 | 2001-12-11 | Medtronic, Inc. | Method for fabricating a planar eversible lattice which forms a stent when everted |
US5888201A (en) * | 1996-02-08 | 1999-03-30 | Schneider (Usa) Inc | Titanium alloy self-expanding stent |
US6027525A (en) * | 1996-05-23 | 2000-02-22 | Samsung Electronics., Ltd. | Flexible self-expandable stent and method for making the same |
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 |
US5861003A (en) * | 1996-10-23 | 1999-01-19 | The Cleveland Clinic Foundation | Apparatus and method for occluding a defect or aperture within body surface |
US6126686A (en) * | 1996-12-10 | 2000-10-03 | Purdue Research Foundation | Artificial vascular valves |
US6287334B1 (en) * | 1996-12-18 | 2001-09-11 | Venpro Corporation | Device for regulating the flow of blood through the blood system |
US5957949A (en) * | 1997-05-01 | 1999-09-28 | World Medical Manufacturing Corp. | Percutaneous placement valve stent |
US6183495B1 (en) * | 1997-05-05 | 2001-02-06 | Micro Therapeutics, Inc. | Wire frame partial flow obstruction device for aneurysm treatment |
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 |
US5876434A (en) * | 1997-07-13 | 1999-03-02 | Litana Ltd. | Implantable medical devices of shape memory alloy |
US6245103B1 (en) * | 1997-08-01 | 2001-06-12 | Schneider (Usa) Inc | Bioabsorbable self-expanding stent |
US6719934B2 (en) * | 1997-08-01 | 2004-04-13 | Boston Scientific Scimed, Inc. | Process for making bioabsorbable self-expanding stent |
US6652582B1 (en) * | 1997-08-01 | 2003-11-25 | Boston Scientific Scimed, Inc. | Bioabsorbable endoprosthesis having porosity for by-product collection |
US6280467B1 (en) * | 1998-02-26 | 2001-08-28 | World Medical Manufacturing Corporation | Delivery system for deployment and endovascular assembly of a multi-stage stented graft |
US6508833B2 (en) * | 1998-06-02 | 2003-01-21 | Cook Incorporated | Multiple-sided intraluminal medical device |
US6200336B1 (en) * | 1998-06-02 | 2001-03-13 | Cook Incorporated | Multiple-sided intraluminal medical device |
US6254636B1 (en) * | 1998-06-26 | 2001-07-03 | St. Jude Medical, Inc. | Single suture biological tissue aortic stentless valve |
US20010039450A1 (en) * | 1999-06-02 | 2001-11-08 | Dusan Pavcnik | Implantable vascular device |
US6299637B1 (en) * | 1999-08-20 | 2001-10-09 | Samuel M. Shaolian | Transluminally implantable venous valve |
US20030130726A1 (en) * | 1999-09-10 | 2003-07-10 | Thorpe Patricia E. | Combination valve and stent for treating vascular reflux |
US6312474B1 (en) * | 1999-09-15 | 2001-11-06 | Bio-Vascular, Inc. | Resorbable implant materials |
US20020188348A1 (en) * | 1999-10-21 | 2002-12-12 | Scimed Life Systems, Inc. | Implantable prosthetic valve |
US6440164B1 (en) * | 1999-10-21 | 2002-08-27 | Scimed Life Systems, Inc. | Implantable prosthetic valve |
US6685739B2 (en) * | 1999-10-21 | 2004-02-03 | Scimed Life Systems, Inc. | Implantable prosthetic valve |
US20040093060A1 (en) * | 1999-11-17 | 2004-05-13 | Jacques Seguin | Prosthetic valve for transluminal delivery |
US20030023303A1 (en) * | 1999-11-19 | 2003-01-30 | Palmaz Julio C. | Valvular prostheses having metal or pseudometallic construction and methods of manufacture |
US6652578B2 (en) * | 1999-12-31 | 2003-11-25 | Abps Venture One, Ltd. | Endoluminal cardiac and venous valve prostheses and methods of manufacture and delivery thereof |
US20030023300A1 (en) * | 1999-12-31 | 2003-01-30 | Bailey Steven R. | Endoluminal cardiac and venous valve prostheses and methods of manufacture and delivery thereof |
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 |
US20030208261A1 (en) * | 2000-03-03 | 2003-11-06 | Thorpe Patricia E. | Bulbous valve and stent for treating vascular reflux |
US6676698B2 (en) * | 2000-06-26 | 2004-01-13 | Rex Medicol, L.P. | Vascular device with valve for approximating vessel wall |
US20020099439A1 (en) * | 2000-09-29 | 2002-07-25 | Schwartz Robert S. | Venous valvuloplasty device and method |
US6503272B2 (en) * | 2001-03-21 | 2003-01-07 | Cordis Corporation | Stent-based venous valves |
US20030191525A1 (en) * | 2002-04-03 | 2003-10-09 | Thornton Sally C. | Artifical valve |
US20030225447A1 (en) * | 2002-05-10 | 2003-12-04 | Majercak David Christopher | Method of making a medical device having a thin wall tubular membrane over a structural frame |
US20030236568A1 (en) * | 2002-05-10 | 2003-12-25 | Hikmat Hojeibane | Multi-lobed frame based unidirectional flow prosthetic implant |
US20040019374A1 (en) * | 2002-05-10 | 2004-01-29 | Hikmat Hojeibane | Frame based unidirectional flow prosthetic implant |
US20040034408A1 (en) * | 2002-05-10 | 2004-02-19 | Majercak David Christopher | Method of placing a tubular membrane on a structural frame |
Cited By (381)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
US20050261669A1 (en) * | 1998-04-30 | 2005-11-24 | Medtronic, Inc. | Intracardiovascular access (ICVA™) system |
US10485976B2 (en) | 1998-04-30 | 2019-11-26 | Medtronic, Inc. | Intracardiovascular access (ICVA™) system |
US8597226B2 (en) | 1998-09-10 | 2013-12-03 | Jenavalve Technology, Inc. | Methods and conduits for flowing blood from a heart chamber to a blood vessel |
US7704222B2 (en) | 1998-09-10 | 2010-04-27 | Jenavalve Technology, Inc. | Methods and conduits for flowing blood from a heart chamber to a blood vessel |
US7736327B2 (en) | 1998-09-10 | 2010-06-15 | Jenavalve Technology, Inc. | Methods and conduits for flowing blood from a heart chamber to a blood vessel |
US20080262602A1 (en) * | 1998-09-10 | 2008-10-23 | Jenavalve Technology, Inc. | Methods and conduits for flowing blood from a heart chamber to a blood vessel |
US8216174B2 (en) | 1998-09-10 | 2012-07-10 | Jenavalve Technology, Inc. | Methods and conduits for flowing blood from a heart chamber to a blood vessel |
US10219901B2 (en) | 1999-11-17 | 2019-03-05 | Medtronic CV Luxembourg S.a.r.l. | Prosthetic valve for transluminal delivery |
US9066799B2 (en) | 1999-11-17 | 2015-06-30 | Medtronic Corevalve Llc | Prosthetic valve for transluminal delivery |
US8876896B2 (en) | 1999-11-17 | 2014-11-04 | Medtronic Corevalve Llc | Prosthetic valve for transluminal delivery |
US8801779B2 (en) | 1999-11-17 | 2014-08-12 | Medtronic Corevalve, Llc | Prosthetic valve for transluminal delivery |
US8016877B2 (en) | 1999-11-17 | 2011-09-13 | Medtronic Corevalve Llc | Prosthetic valve for transluminal delivery |
US8603159B2 (en) | 1999-11-17 | 2013-12-10 | Medtronic Corevalve, Llc | Prosthetic valve for transluminal delivery |
US8721708B2 (en) | 1999-11-17 | 2014-05-13 | Medtronic Corevalve Llc | Prosthetic valve for transluminal delivery |
US7896913B2 (en) | 2000-02-28 | 2011-03-01 | Jenavalve Technology, Inc. | Anchoring system for implantable heart valve prostheses |
USRE45130E1 (en) | 2000-02-28 | 2014-09-09 | Jenavalve Technology Gmbh | Device for fastening and anchoring cardiac valve prostheses |
US8777980B2 (en) | 2000-06-30 | 2014-07-15 | Medtronic, Inc. | Intravascular filter with debris entrapment mechanism |
US8092487B2 (en) | 2000-06-30 | 2012-01-10 | Medtronic, Inc. | Intravascular filter with debris entrapment mechanism |
US10278805B2 (en) | 2000-08-18 | 2019-05-07 | Atritech, Inc. | Expandable implant devices for filtering blood flow from atrial appendages |
US7776053B2 (en) | 2000-10-26 | 2010-08-17 | Boston Scientific Scimed, Inc. | Implantable valve system |
US8951280B2 (en) | 2000-11-09 | 2015-02-10 | Medtronic, Inc. | Cardiac valve procedure methods and devices |
US8038708B2 (en) | 2001-02-05 | 2011-10-18 | Cook Medical Technologies Llc | Implantable device with remodelable material and covering material |
US20070162103A1 (en) * | 2001-02-05 | 2007-07-12 | Cook Incorporated | Implantable device with remodelable material and covering material |
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 |
US8956402B2 (en) | 2001-06-29 | 2015-02-17 | Medtronic, Inc. | Apparatus for replacing a cardiac valve |
US8070801B2 (en) | 2001-06-29 | 2011-12-06 | Medtronic, Inc. | Method and apparatus for resecting and replacing an aortic valve |
US9889002B2 (en) | 2001-08-03 | 2018-02-13 | Jenavalve Technology, Inc. | Devices useful for implantation at a heart valve |
US11007052B2 (en) | 2001-08-03 | 2021-05-18 | Jenavalve Technology, Inc. | Devices useful for implantation at a heart valve |
US8206437B2 (en) | 2001-08-03 | 2012-06-26 | Philipp Bonhoeffer | Implant implantation unit and procedure for implanting the unit |
US8216301B2 (en) | 2001-08-03 | 2012-07-10 | Philipp Bonhoeffer | Implant implantation unit |
US9949824B2 (en) | 2001-08-03 | 2018-04-24 | Jenavalve Technology, Inc. | Devices useful for implantation at a heart valve |
US8585756B2 (en) | 2001-08-03 | 2013-11-19 | Jenavalve Technology, Inc. | Methods of treating valves |
US8579965B2 (en) | 2001-08-03 | 2013-11-12 | Jenavalve Technology, Inc. | Methods of implanting an implantation device |
US8303653B2 (en) | 2001-08-03 | 2012-11-06 | Philipp Bonhoeffer | Implant implantation unit and procedure for implanting the unit |
US9539088B2 (en) | 2001-09-07 | 2017-01-10 | Medtronic, Inc. | Fixation band for affixing a prosthetic heart valve to tissue |
US10342657B2 (en) | 2001-09-07 | 2019-07-09 | Medtronic, Inc. | Fixation band for affixing a prosthetic heart valve to tissue |
US20060089708A1 (en) * | 2002-02-20 | 2006-04-27 | Osse Francisco J | Venous bi-valve |
US7682385B2 (en) | 2002-04-03 | 2010-03-23 | Boston Scientific Corporation | Artificial valve |
US7780627B2 (en) | 2002-12-30 | 2010-08-24 | Boston Scientific Scimed, Inc. | Valve treatment catheter and methods |
US20050075729A1 (en) * | 2003-10-06 | 2005-04-07 | Nguyen Tuoc Tan | Minimally invasive valve replacement system |
US9579194B2 (en) | 2003-10-06 | 2017-02-28 | Medtronic ATS Medical, Inc. | Anchoring structure with concave landing zone |
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 |
US8128681B2 (en) | 2003-12-19 | 2012-03-06 | Boston Scientific Scimed, Inc. | Venous valve apparatus, system, and method |
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 |
US10426608B2 (en) | 2003-12-23 | 2019-10-01 | Boston Scientific Scimed, Inc. | Repositionable heart valve |
US9585749B2 (en) | 2003-12-23 | 2017-03-07 | Boston Scientific Scimed, Inc. | Replacement heart valve assembly |
US8052749B2 (en) | 2003-12-23 | 2011-11-08 | Sadra Medical, Inc. | Methods and apparatus for endovascular heart valve replacement comprising tissue grasping elements |
US9308085B2 (en) | 2003-12-23 | 2016-04-12 | Boston Scientific Scimed, Inc. | Repositionable heart valve and method |
US10716663B2 (en) | 2003-12-23 | 2020-07-21 | Boston Scientific Scimed, Inc. | Methods and apparatus for performing valvuloplasty |
US11278398B2 (en) | 2003-12-23 | 2022-03-22 | Boston Scientific Scimed, Inc. | Methods and apparatus for endovascular heart valve replacement comprising tissue grasping elements |
US9320599B2 (en) | 2003-12-23 | 2016-04-26 | Boston Scientific Scimed, Inc. | Methods and apparatus for endovascularly replacing a heart valve |
US9358106B2 (en) | 2003-12-23 | 2016-06-07 | Boston Scientific Scimed Inc. | Methods and apparatus for performing valvuloplasty |
US11285002B2 (en) | 2003-12-23 | 2022-03-29 | Boston Scientific Scimed, Inc. | Methods and apparatus for endovascularly replacing a heart valve |
US9861476B2 (en) | 2003-12-23 | 2018-01-09 | Boston Scientific Scimed Inc. | Leaflet engagement elements and methods for use thereof |
US9277991B2 (en) | 2003-12-23 | 2016-03-08 | Boston Scientific Scimed, Inc. | Low profile heart valve and delivery system |
US10478289B2 (en) | 2003-12-23 | 2019-11-19 | Boston Scientific Scimed, Inc. | Replacement valve and anchor |
US8182528B2 (en) | 2003-12-23 | 2012-05-22 | Sadra Medical, Inc. | Locking heart valve anchor |
US9358110B2 (en) | 2003-12-23 | 2016-06-07 | Boston Scientific Scimed, Inc. | Medical devices and delivery systems for delivering medical devices |
US8828078B2 (en) | 2003-12-23 | 2014-09-09 | Sadra Medical, Inc. | Methods and apparatus for endovascular heart valve replacement comprising tissue grasping elements |
US9956075B2 (en) | 2003-12-23 | 2018-05-01 | Boston Scientific Scimed Inc. | Methods and apparatus for endovascularly replacing a heart valve |
US9393113B2 (en) | 2003-12-23 | 2016-07-19 | Boston Scientific Scimed Inc. | Retrievable heart valve anchor and method |
US9526609B2 (en) | 2003-12-23 | 2016-12-27 | Boston Scientific Scimed, Inc. | Methods and apparatus for endovascularly replacing a patient's heart valve |
US8231670B2 (en) | 2003-12-23 | 2012-07-31 | Sadra Medical, Inc. | Repositionable heart valve and method |
US8246678B2 (en) | 2003-12-23 | 2012-08-21 | Sadra Medicl, Inc. | Methods and apparatus for endovascularly replacing a patient's heart valve |
US8252052B2 (en) | 2003-12-23 | 2012-08-28 | Sadra Medical, Inc. | Methods and apparatus for endovascularly replacing a patient's heart valve |
US9532872B2 (en) | 2003-12-23 | 2017-01-03 | Boston Scientific Scimed, Inc. | Systems and methods for delivering a medical implant |
US10413409B2 (en) | 2003-12-23 | 2019-09-17 | Boston Scientific Scimed, Inc. | Systems and methods for delivering a medical implant |
US10413412B2 (en) | 2003-12-23 | 2019-09-17 | Boston Scientific Scimed, Inc. | Methods and apparatus for endovascularly replacing a heart valve |
US11696825B2 (en) | 2003-12-23 | 2023-07-11 | Boston Scientific Scimed, Inc. | Replacement valve and anchor |
US11185408B2 (en) | 2003-12-23 | 2021-11-30 | Boston Scientific Scimed, Inc. | Methods and apparatus for endovascular heart valve replacement comprising tissue grasping elements |
US8623078B2 (en) | 2003-12-23 | 2014-01-07 | Sadra Medical, Inc. | Replacement valve and anchor |
US8343213B2 (en) | 2003-12-23 | 2013-01-01 | Sadra Medical, Inc. | Leaflet engagement elements and methods for use thereof |
US10357359B2 (en) | 2003-12-23 | 2019-07-23 | Boston Scientific Scimed Inc | Methods and apparatus for endovascularly replacing a patient's heart valve |
US9585750B2 (en) | 2003-12-23 | 2017-03-07 | Boston Scientific Scimed, Inc. | Methods and apparatus for endovascularly replacing a patient's heart valve |
US8840662B2 (en) | 2003-12-23 | 2014-09-23 | Sadra Medical, Inc. | Repositionable heart valve and method |
US10335273B2 (en) | 2003-12-23 | 2019-07-02 | Boston Scientific Scimed Inc. | Leaflet engagement elements and methods for use thereof |
US10314695B2 (en) | 2003-12-23 | 2019-06-11 | Boston Scientific Scimed Inc. | Methods and apparatus for endovascular heart valve replacement comprising tissue grasping elements |
US9872768B2 (en) | 2003-12-23 | 2018-01-23 | Boston Scientific Scimed, Inc. | Medical devices and delivery systems for delivering medical devices |
US9011521B2 (en) | 2003-12-23 | 2015-04-21 | Sadra Medical, Inc. | Methods and apparatus for endovascularly replacing a patient's heart valve |
US9005273B2 (en) | 2003-12-23 | 2015-04-14 | Sadra Medical, Inc. | Assessing the location and performance of replacement heart valves |
US10925724B2 (en) | 2003-12-23 | 2021-02-23 | Boston Scientific Scimed, Inc. | Replacement valve and anchor |
US8623076B2 (en) | 2003-12-23 | 2014-01-07 | Sadra Medical, Inc. | Low profile heart valve and delivery system |
US8603160B2 (en) | 2003-12-23 | 2013-12-10 | Sadra Medical, Inc. | Method of using a retrievable heart valve anchor with a sheath |
US10206774B2 (en) | 2003-12-23 | 2019-02-19 | Boston Scientific Scimed Inc. | Low profile heart valve and delivery system |
US8840663B2 (en) | 2003-12-23 | 2014-09-23 | Sadra Medical, Inc. | Repositionable heart valve method |
US10258465B2 (en) | 2003-12-23 | 2019-04-16 | Boston Scientific Scimed Inc. | Methods and apparatus for endovascular heart valve replacement comprising tissue grasping elements |
US8894703B2 (en) | 2003-12-23 | 2014-11-25 | Sadra Medical, Inc. | Systems and methods for delivering a medical implant |
US8858620B2 (en) | 2003-12-23 | 2014-10-14 | Sadra Medical Inc. | Methods and apparatus for endovascularly replacing a heart valve |
US8579962B2 (en) | 2003-12-23 | 2013-11-12 | Sadra Medical, Inc. | Methods and apparatus for performing valvuloplasty |
US9066798B2 (en) | 2004-02-09 | 2015-06-30 | Cook Medical Technologies Llc | Woven implantable device |
US8337545B2 (en) | 2004-02-09 | 2012-12-25 | Cook Medical Technologies Llc | Woven implantable device |
US8109996B2 (en) | 2004-03-03 | 2012-02-07 | Sorin Biomedica Cardio, S.R.L. | Minimally-invasive cardiac-valve prosthesis |
US8535373B2 (en) | 2004-03-03 | 2013-09-17 | Sorin Group Italia S.R.L. | Minimally-invasive cardiac-valve prosthesis |
US9867695B2 (en) | 2004-03-03 | 2018-01-16 | Sorin Group Italia S.R.L. | Minimally-invasive cardiac-valve prosthesis |
US9775704B2 (en) | 2004-04-23 | 2017-10-03 | Medtronic3F Therapeutics, Inc. | Implantable valve prosthesis |
US9744035B2 (en) | 2004-06-16 | 2017-08-29 | Boston Scientific Scimed, Inc. | Everting heart valve |
US8992608B2 (en) | 2004-06-16 | 2015-03-31 | Sadra Medical, Inc. | Everting heart valve |
US11484405B2 (en) | 2004-06-16 | 2022-11-01 | Boston Scientific Scimed, Inc. | Everting heart valve |
US8668733B2 (en) | 2004-06-16 | 2014-03-11 | Sadra Medical, Inc. | Everting heart valve |
US20060004442A1 (en) * | 2004-06-30 | 2006-01-05 | Benjamin Spenser | Paravalvular leak detection, sealing, and prevention |
US8002824B2 (en) | 2004-09-02 | 2011-08-23 | Boston Scientific Scimed, Inc. | 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 |
US8328868B2 (en) | 2004-11-05 | 2012-12-11 | Sadra Medical, Inc. | Medical devices and delivery systems for delivering medical devices |
US10531952B2 (en) | 2004-11-05 | 2020-01-14 | Boston Scientific Scimed, Inc. | Medical devices and delivery systems for delivering medical devices |
US8617236B2 (en) | 2004-11-05 | 2013-12-31 | Sadra Medical, Inc. | Medical devices and delivery systems for delivering medical devices |
US20100114300A1 (en) * | 2004-12-01 | 2010-05-06 | Cook Incorporated | Medical device with leak path |
US9788945B2 (en) | 2005-01-20 | 2017-10-17 | Jenavalve Technology, Inc. | Systems for implanting an endoprosthesis |
US8679174B2 (en) | 2005-01-20 | 2014-03-25 | JenaValve Technology, GmbH | Catheter for the transvascular implantation of prosthetic heart valves |
US9775705B2 (en) | 2005-01-20 | 2017-10-03 | Jenavalve Technology, Inc. | Methods of implanting an endoprosthesis |
US11517431B2 (en) | 2005-01-20 | 2022-12-06 | Jenavalve Technology, Inc. | Catheter system for implantation of prosthetic heart valves |
US10492906B2 (en) | 2005-01-20 | 2019-12-03 | Jenavalve Technology, Inc. | Catheter system for implantation of prosthetic heart valves |
US7854755B2 (en) | 2005-02-01 | 2010-12-21 | Boston Scientific Scimed, Inc. | Vascular catheter, system, and method |
US9622859B2 (en) | 2005-02-01 | 2017-04-18 | Boston Scientific Scimed, Inc. | Filter system and method |
US7878966B2 (en) | 2005-02-04 | 2011-02-01 | Boston Scientific Scimed, Inc. | Ventricular assist and support device |
US7780722B2 (en) | 2005-02-07 | 2010-08-24 | Boston Scientific Scimed, Inc. | Venous valve apparatus, system, and method |
US7670368B2 (en) * | 2005-02-07 | 2010-03-02 | Boston Scientific Scimed, Inc. | Venous valve apparatus, system, and method |
US8920492B2 (en) | 2005-02-10 | 2014-12-30 | Sorin Group Italia S.R.L. | Cardiac valve prosthesis |
US8540768B2 (en) | 2005-02-10 | 2013-09-24 | Sorin Group Italia S.R.L. | Cardiac valve prosthesis |
US9895223B2 (en) | 2005-02-10 | 2018-02-20 | Sorin Group Italia S.R.L. | Cardiac valve prosthesis |
US8539662B2 (en) | 2005-02-10 | 2013-09-24 | Sorin Group Italia S.R.L. | Cardiac-valve prosthesis |
US9486313B2 (en) | 2005-02-10 | 2016-11-08 | Sorin Group Italia S.R.L. | Cardiac valve prosthesis |
US9808341B2 (en) | 2005-02-23 | 2017-11-07 | Boston Scientific Scimed Inc. | Valve apparatus, system and method |
US9370419B2 (en) | 2005-02-23 | 2016-06-21 | Boston Scientific Scimed, Inc. | Valve apparatus, system and method |
US8197534B2 (en) | 2005-03-31 | 2012-06-12 | Cook Medical Technologies Llc | Valve device with inflatable chamber |
US9017397B2 (en) | 2005-03-31 | 2015-04-28 | Cook Medical Technologies Llc | Valve device with inflatable chamber |
US20060235512A1 (en) * | 2005-03-31 | 2006-10-19 | Cook Incorporated | Valve device with inflatable chamber |
US9861473B2 (en) | 2005-04-15 | 2018-01-09 | Boston Scientific Scimed Inc. | Valve apparatus, system and method |
US8512399B2 (en) | 2005-04-15 | 2013-08-20 | Boston Scientific Scimed, Inc. | Valve apparatus, system and method |
US7722666B2 (en) | 2005-04-15 | 2010-05-25 | Boston Scientific Scimed, Inc. | Valve apparatus, system and method |
US10549101B2 (en) | 2005-04-25 | 2020-02-04 | Cardiac Pacemakers, Inc. | Method and apparatus for pacing during revascularization |
US9649495B2 (en) | 2005-04-25 | 2017-05-16 | Cardiac Pacemakers, Inc. | Method and apparatus for pacing during revascularization |
US9415225B2 (en) | 2005-04-25 | 2016-08-16 | Cardiac Pacemakers, Inc. | Method and apparatus for pacing during revascularization |
US8226710B2 (en) | 2005-05-13 | 2012-07-24 | Medtronic Corevalve, Inc. | Heart valve prosthesis and methods of manufacture and use |
USD732666S1 (en) | 2005-05-13 | 2015-06-23 | Medtronic Corevalve, Inc. | Heart valve prosthesis |
US9060857B2 (en) | 2005-05-13 | 2015-06-23 | Medtronic Corevalve Llc | Heart valve prosthesis and methods of manufacture and use |
USD812226S1 (en) | 2005-05-13 | 2018-03-06 | Medtronic Corevalve Llc | Heart valve prosthesis |
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 |
US11337812B2 (en) | 2005-06-10 | 2022-05-24 | Boston Scientific Scimed, Inc. | Venous valve, system and method |
US20070027460A1 (en) * | 2005-07-27 | 2007-02-01 | Cook Incorporated | Implantable remodelable materials comprising magnetic material |
US20070027535A1 (en) * | 2005-07-28 | 2007-02-01 | Cook Incorporated | Implantable thromboresistant valve |
US20070027528A1 (en) * | 2005-07-29 | 2007-02-01 | Cook Incorporated | Elliptical implantable device |
US20070061002A1 (en) * | 2005-09-01 | 2007-03-15 | Cook Incorporated | Attachment of material to an implantable frame by cross-linking |
US8672997B2 (en) | 2005-09-21 | 2014-03-18 | Boston Scientific Scimed, Inc. | Valve with sinus |
US7951189B2 (en) | 2005-09-21 | 2011-05-31 | Boston Scientific Scimed, Inc. | Venous valve, system, and method with sinus pocket |
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 |
US8460365B2 (en) | 2005-09-21 | 2013-06-11 | Boston Scientific Scimed, Inc. | Venous valve, system, and method with sinus pocket |
US8092521B2 (en) | 2005-10-28 | 2012-01-10 | Jenavalve Technology, Inc. | Device for the implantation and fixation of prosthetic valves |
US11116628B2 (en) | 2005-10-28 | 2021-09-14 | Jenavalve Technology, Inc. | Device for the implantation and fixation of prosthetic valves |
US8834561B2 (en) | 2005-10-28 | 2014-09-16 | Jenavalve Technology Gmbh | Device for the implantation and fixation of prosthetic valves |
US8551160B2 (en) | 2005-10-28 | 2013-10-08 | Jenavalve Technology, Inc. | Device for the implantation and fixation of prosthetic valves |
USRE45962E1 (en) | 2005-10-28 | 2016-04-05 | Jenavalve Technology Gmbh | Device for the implantation and fixation of prosthetic valves |
US10363134B2 (en) | 2005-10-28 | 2019-07-30 | Jenavalve Technology, Inc. | Device for the implantation and fixation of prosthetic valves |
USRE45790E1 (en) | 2005-10-28 | 2015-11-03 | Jenavalve Technology Gmbh | Device for the implantation and fixation of prosthetic valves |
US9402717B2 (en) | 2005-10-28 | 2016-08-02 | Jenavalve Technology, Inc. | Device for the implantation and fixation of prosthetic valves |
US9044320B2 (en) | 2005-10-28 | 2015-06-02 | Jenavalve Technology Gmbh | Device for the implantation and fixation of prosthetic valves |
US9855142B2 (en) | 2005-10-28 | 2018-01-02 | JenaValve Technologies, Inc. | Device for the implantation and fixation of prosthetic valves |
US8062355B2 (en) | 2005-11-04 | 2011-11-22 | Jenavalve Technology, Inc. | Self-expandable medical instrument for treating defects in a patient's heart |
US10299922B2 (en) | 2005-12-22 | 2019-05-28 | Symetis Sa | Stent-valves for valve replacement and associated methods and systems for surgery |
US10314701B2 (en) | 2005-12-22 | 2019-06-11 | Symetis Sa | Stent-valves for valve replacement and associated methods and systems for surgery |
US10265167B2 (en) | 2005-12-22 | 2019-04-23 | Symetis Sa | Stent-valves for valve replacement and associated methods and systems for surgery |
US9839515B2 (en) | 2005-12-22 | 2017-12-12 | Symetis, SA | Stent-valves for valve replacement and associated methods and systems for surgery |
US8840657B2 (en) * | 2006-01-18 | 2014-09-23 | Cook Medical Technologies Llc | Self expanding stent |
US20070191922A1 (en) * | 2006-01-18 | 2007-08-16 | William A. Cook Australia Pty. Ltd. | Self expanding stent |
US7799038B2 (en) | 2006-01-20 | 2010-09-21 | Boston Scientific Scimed, Inc. | Translumenal apparatus, system, and method |
US20080046071A1 (en) * | 2006-08-21 | 2008-02-21 | Dusan Pavcnik | Biomedical valve devices, support frames for use in such devices, and related methods |
US8257429B2 (en) | 2006-08-21 | 2012-09-04 | Oregon Health & Science University | Biomedical valve devices, support frames for use in such devices, and related methods |
US8992598B2 (en) | 2006-08-21 | 2015-03-31 | Oregan Health And Science University | Biomedical valve devices, support frames for use in such devices, and related methods |
US9301834B2 (en) | 2006-09-19 | 2016-04-05 | Medtronic Ventor Technologies Ltd. | Sinus-engaging valve fixation member |
US8834564B2 (en) | 2006-09-19 | 2014-09-16 | Medtronic, Inc. | Sinus-engaging valve fixation member |
US8771346B2 (en) | 2006-09-19 | 2014-07-08 | Medtronic Ventor Technologies Ltd. | Valve prosthetic fixation techniques using sandwiching |
US9827097B2 (en) | 2006-09-19 | 2017-11-28 | Medtronic Ventor Technologies Ltd. | Sinus-engaging valve fixation member |
US10004601B2 (en) | 2006-09-19 | 2018-06-26 | Medtronic Ventor Technologies Ltd. | Valve prosthesis fixation techniques using sandwiching |
US11304800B2 (en) | 2006-09-19 | 2022-04-19 | Medtronic Ventor Technologies Ltd. | Sinus-engaging valve fixation member |
US11304801B2 (en) | 2006-09-19 | 2022-04-19 | Medtronic Ventor Technologies Ltd. | Sinus-engaging valve fixation member |
US10543077B2 (en) | 2006-09-19 | 2020-01-28 | Medtronic, Inc. | Sinus-engaging valve fixation member |
US8771345B2 (en) | 2006-09-19 | 2014-07-08 | Medtronic Ventor Technologies Ltd. | Valve prosthesis fixation techniques using sandwiching |
US9138312B2 (en) | 2006-09-19 | 2015-09-22 | Medtronic Ventor Technologies Ltd. | Valve prostheses |
US8747460B2 (en) | 2006-09-19 | 2014-06-10 | Medtronic Ventor Technologies Ltd. | Methods for implanting a valve prothesis |
US11304802B2 (en) | 2006-09-19 | 2022-04-19 | Medtronic Ventor Technologies Ltd. | Sinus-engaging valve fixation member |
US9387071B2 (en) | 2006-09-19 | 2016-07-12 | Medtronic, Inc. | Sinus-engaging valve fixation member |
US9642704B2 (en) | 2006-09-19 | 2017-05-09 | Medtronic Ventor Technologies Ltd. | Catheter for implanting a valve prosthesis |
US9913714B2 (en) | 2006-09-19 | 2018-03-13 | Medtronic, Inc. | Sinus-engaging valve fixation member |
US8414643B2 (en) | 2006-09-19 | 2013-04-09 | Medtronic Ventor Technologies Ltd. | Sinus-engaging valve fixation member |
US8784478B2 (en) | 2006-10-16 | 2014-07-22 | Medtronic Corevalve, Inc. | Transapical delivery system with ventruculo-arterial overlfow bypass |
US8747459B2 (en) | 2006-12-06 | 2014-06-10 | Medtronic Corevalve Llc | System and method for transapical delivery of an annulus anchored self-expanding valve |
US9295550B2 (en) | 2006-12-06 | 2016-03-29 | Medtronic CV Luxembourg S.a.r.l. | Methods for delivering a self-expanding valve |
US8348999B2 (en) | 2007-01-08 | 2013-01-08 | California Institute Of Technology | In-situ formation of a valve |
US8133270B2 (en) | 2007-01-08 | 2012-03-13 | California Institute Of Technology | In-situ formation of a valve |
US20100174361A1 (en) * | 2007-01-29 | 2010-07-08 | Cook Incorporated | Prosthetic valve with semi-rigid and flexible leaflets |
US20080183279A1 (en) * | 2007-01-29 | 2008-07-31 | Cook Incorporated | Prosthetic Valve with Slanted Leaflet Design |
US20080183280A1 (en) * | 2007-01-29 | 2008-07-31 | Cook Incorporated | Artificial venous valve with discrete shaping members |
US7678144B2 (en) | 2007-01-29 | 2010-03-16 | Cook Incorporated | Prosthetic valve with slanted leaflet design |
US8303649B2 (en) | 2007-01-29 | 2012-11-06 | Cook Medical Technologies Llc | Artificial venous valve with discrete shaping members |
US8470023B2 (en) | 2007-02-05 | 2013-06-25 | Boston Scientific Scimed, Inc. | Percutaneous valve, system, and method |
US11504239B2 (en) | 2007-02-05 | 2022-11-22 | 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 |
US7967853B2 (en) | 2007-02-05 | 2011-06-28 | 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 |
US9504568B2 (en) | 2007-02-16 | 2016-11-29 | Medtronic, Inc. | Replacement prosthetic heart valves and methods of implantation |
US9918835B2 (en) | 2007-04-13 | 2018-03-20 | Jenavalve Technology, Inc. | Medical device for treating a heart valve insufficency |
US10543084B2 (en) | 2007-04-13 | 2020-01-28 | Jenavalve Technology, Inc. | Medical device for treating a heart valve insufficiency |
US9138315B2 (en) | 2007-04-13 | 2015-09-22 | Jenavalve Technology Gmbh | Medical device for treating a heart valve insufficiency or stenosis |
US9445896B2 (en) | 2007-04-13 | 2016-09-20 | Jenavalve Technology, Inc. | Methods for treating a heart valve insufficiency or stenosis |
US7914575B2 (en) | 2007-04-13 | 2011-03-29 | Jenavalve Technology, Inc. | Medical device for treating a heart valve insufficiency |
US11357624B2 (en) | 2007-04-13 | 2022-06-14 | Jenavalve Technology, Inc. | Medical device for treating a heart valve insufficiency |
US9295551B2 (en) | 2007-04-13 | 2016-03-29 | Jenavalve Technology Gmbh | Methods of implanting an endoprosthesis |
US8685085B2 (en) | 2007-04-13 | 2014-04-01 | JenaValve Technologies GmbH | Medical device for treating a heart valve insufficiency |
US9339386B2 (en) | 2007-04-13 | 2016-05-17 | Jenavalve Technology, Inc. | Medical device for treating a heart valve insufficency |
US7896915B2 (en) | 2007-04-13 | 2011-03-01 | Jenavalve Technology, Inc. | Medical device for treating a heart valve insufficiency |
US9237886B2 (en) | 2007-04-20 | 2016-01-19 | Medtronic, Inc. | Implant for treatment of a heart valve, in particular a mitral valve, material including such an implant, and material for insertion thereof |
US9585754B2 (en) | 2007-04-20 | 2017-03-07 | Medtronic, Inc. | Implant for treatment of a heart valve, in particular a mitral valve, material including such an implant, and material for insertion thereof |
US8828079B2 (en) | 2007-07-26 | 2014-09-09 | Boston Scientific Scimed, Inc. | Circulatory valve, system and method |
US10188516B2 (en) | 2007-08-20 | 2019-01-29 | Medtronic Ventor Technologies Ltd. | Stent loading tool and method for use thereof |
US20090062907A1 (en) * | 2007-08-31 | 2009-03-05 | Quijano Rodolfo C | Self-expanding valve for the venous system |
US10856970B2 (en) | 2007-10-10 | 2020-12-08 | Medtronic Ventor Technologies Ltd. | Prosthetic heart valve for transfemoral delivery |
US10966823B2 (en) | 2007-10-12 | 2021-04-06 | Sorin Group Italia S.R.L. | Expandable valve prosthesis with sealing mechanism |
US9848981B2 (en) | 2007-10-12 | 2017-12-26 | Mayo Foundation For Medical Education And Research | Expandable valve prosthesis with sealing mechanism |
US8137394B2 (en) | 2007-12-21 | 2012-03-20 | 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 |
US8414641B2 (en) | 2007-12-21 | 2013-04-09 | Boston Scientific Scimed, Inc. | Valve with delayed leaflet deployment |
US8506621B2 (en) | 2008-01-08 | 2013-08-13 | Cook Medical Technologies Llc | Flow-deflecting medical device |
US8100962B2 (en) | 2008-01-08 | 2012-01-24 | Cook Medical Technologies Llc | Flow-deflecting prosthesis for treating venous disease |
US20090177270A1 (en) * | 2008-01-08 | 2009-07-09 | Cook Incorporated | Flow-Deflecting Prosthesis for Treating Venous Disease |
US9393115B2 (en) | 2008-01-24 | 2016-07-19 | Medtronic, Inc. | Delivery systems and methods of implantation for prosthetic heart valves |
US10646335B2 (en) | 2008-01-24 | 2020-05-12 | Medtronic, Inc. | Stents for prosthetic heart valves |
US10639182B2 (en) | 2008-01-24 | 2020-05-05 | Medtronic, Inc. | Delivery systems and methods of implantation for prosthetic heart valves |
US9339382B2 (en) | 2008-01-24 | 2016-05-17 | Medtronic, Inc. | Stents for prosthetic heart valves |
US8157853B2 (en) | 2008-01-24 | 2012-04-17 | Medtronic, Inc. | Delivery systems and methods of implantation for prosthetic heart valves |
US8157852B2 (en) | 2008-01-24 | 2012-04-17 | Medtronic, Inc. | Delivery systems and methods of implantation for prosthetic heart valves |
US10820993B2 (en) | 2008-01-24 | 2020-11-03 | Medtronic, Inc. | Stents for prosthetic heart valves |
US7972378B2 (en) | 2008-01-24 | 2011-07-05 | Medtronic, Inc. | Stents for prosthetic heart valves |
US10016274B2 (en) | 2008-01-24 | 2018-07-10 | Medtronic, Inc. | Stent for prosthetic heart valves |
US10758343B2 (en) | 2008-01-24 | 2020-09-01 | Medtronic, Inc. | Stent for prosthetic heart valves |
US9149358B2 (en) | 2008-01-24 | 2015-10-06 | Medtronic, Inc. | Delivery systems for prosthetic heart valves |
US11607311B2 (en) | 2008-01-24 | 2023-03-21 | Medtronic, Inc. | Stents for prosthetic heart valves |
US11259919B2 (en) | 2008-01-24 | 2022-03-01 | Medtronic, Inc. | Stents for prosthetic heart valves |
US11786367B2 (en) | 2008-01-24 | 2023-10-17 | Medtronic, Inc. | Stents for prosthetic heart valves |
US11284999B2 (en) | 2008-01-24 | 2022-03-29 | Medtronic, Inc. | Stents for prosthetic heart valves |
US9925079B2 (en) | 2008-01-24 | 2018-03-27 | Medtronic, Inc. | Delivery systems and methods of implantation for prosthetic heart valves |
US11083573B2 (en) | 2008-01-24 | 2021-08-10 | Medtronic, Inc. | Delivery systems and methods of implantation for prosthetic heart valves |
US8685077B2 (en) | 2008-01-24 | 2014-04-01 | Medtronics, Inc. | Delivery systems and methods of implantation for prosthetic heart valves |
US11951007B2 (en) | 2008-01-24 | 2024-04-09 | Medtronic, Inc. | Delivery systems and methods of implantation for prosthetic heart valves |
US8673000B2 (en) | 2008-01-24 | 2014-03-18 | Medtronic, Inc. | Stents for prosthetic heart valves |
US20090222085A1 (en) * | 2008-02-22 | 2009-09-03 | University Of Iowa Research Foundation | Cellulose Based Heart Valve Prosthesis |
US8017396B2 (en) | 2008-02-22 | 2011-09-13 | Vijay Kumar | Cellulose based heart valve prosthesis |
US9877828B2 (en) | 2008-02-26 | 2018-01-30 | Jenavalve Technology, Inc. | Stent for the positioning and anchoring of a valvular prosthesis in an implantation site in the heart of a patient |
US10154901B2 (en) | 2008-02-26 | 2018-12-18 | Jenavalve Technology, Inc. | Stent for the positioning and anchoring of a valvular prosthesis in an implantation site in the heart of a patient |
US9439759B2 (en) | 2008-02-26 | 2016-09-13 | Jenavalve Technology, Inc. | Endoprosthesis for implantation in the heart of a patient |
US9265631B2 (en) | 2008-02-26 | 2016-02-23 | 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 |
US10575947B2 (en) | 2008-02-26 | 2020-03-03 | Jenavalve Technology, Inc. | Stent for the positioning and anchoring of a valvular prosthesis in an implantation site in the heart of a patient |
US9987133B2 (en) | 2008-02-26 | 2018-06-05 | Jenavalve Technology, Inc. | Stent for the positioning and anchoring of a valvular prosthesis in an implantation site in the heart of a patient |
US9044318B2 (en) | 2008-02-26 | 2015-06-02 | Jenavalve Technology Gmbh | Stent for the positioning and anchoring of a valvular prosthesis |
US9867699B2 (en) | 2008-02-26 | 2018-01-16 | Jenavalve Technology, Inc. | Endoprosthesis for implantation in the heart of a patient |
US8465540B2 (en) | 2008-02-26 | 2013-06-18 | Jenavalve Technology, Inc. | Stent for the positioning and anchoring of a valvular prosthesis |
US10702382B2 (en) | 2008-02-26 | 2020-07-07 | Jenavalve Technology, Inc. | Stent for the positioning and anchoring of a valvular prosthesis in an implantation site in the heart of a patient |
US8790395B2 (en) | 2008-02-26 | 2014-07-29 | Jenavalve Technology Gmbh | Stent for the positioning and anchoring of a valvular prosthesis in an implantation site in the heart of a patient |
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 |
US8317858B2 (en) | 2008-02-26 | 2012-11-27 | Jenavalve Technology, Inc. | Stent for the positioning and anchoring of a valvular prosthesis in an implantation site in the heart of a patient |
US8398704B2 (en) | 2008-02-26 | 2013-03-19 | Jenavalve Technology, Inc. | Stent for the positioning and anchoring of a valvular prosthesis in an implantation site in the heart of a patient |
US9168130B2 (en) | 2008-02-26 | 2015-10-27 | Jenavalve Technology Gmbh | Stent for the positioning and anchoring of a valvular prosthesis in an implantation site in the heart of a patient |
US9707075B2 (en) | 2008-02-26 | 2017-07-18 | Jenavalve Technology, Inc. | Endoprosthesis for implantation 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 |
US8430927B2 (en) | 2008-04-08 | 2013-04-30 | Medtronic, Inc. | Multiple orifice implantable heart valve and methods of implantation |
US10245142B2 (en) | 2008-04-08 | 2019-04-02 | Medtronic, Inc. | Multiple orifice implantable heart valve and methods of implantation |
US8840661B2 (en) | 2008-05-16 | 2014-09-23 | Sorin Group Italia S.R.L. | Atraumatic prosthetic heart valve prosthesis |
US10806570B2 (en) | 2008-09-15 | 2020-10-20 | Medtronic, Inc. | Prosthetic heart valve having identifiers for aiding in radiographic positioning |
US11026786B2 (en) | 2008-09-15 | 2021-06-08 | Medtronic, Inc. | Prosthetic heart valve having identifiers for aiding in radiographic positioning |
US8998981B2 (en) | 2008-09-15 | 2015-04-07 | Medtronic, Inc. | Prosthetic heart valve having identifiers for aiding in radiographic positioning |
US9943407B2 (en) | 2008-09-15 | 2018-04-17 | Medtronic, Inc. | Prosthetic heart valve having identifiers for aiding in radiographic positioning |
US11166815B2 (en) | 2008-09-17 | 2021-11-09 | Medtronic CV Luxembourg S.a.r.l | Delivery system for deployment of medical devices |
US10321997B2 (en) | 2008-09-17 | 2019-06-18 | Medtronic CV Luxembourg S.a.r.l. | Delivery system for deployment of medical devices |
US8721714B2 (en) | 2008-09-17 | 2014-05-13 | Medtronic Corevalve Llc | Delivery system for deployment of medical devices |
US9532873B2 (en) | 2008-09-17 | 2017-01-03 | Medtronic CV Luxembourg S.a.r.l. | Methods for deployment of medical devices |
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 |
US20100100167A1 (en) * | 2008-10-17 | 2010-04-22 | Georg Bortlein | Delivery system for deployment of medical devices |
US10098733B2 (en) | 2008-12-23 | 2018-10-16 | Sorin Group Italia S.R.L. | Expandable prosthetic valve having anchoring appendages |
US8834563B2 (en) | 2008-12-23 | 2014-09-16 | Sorin Group Italia S.R.L. | Expandable prosthetic valve having anchoring appendages |
US20160151159A1 (en) * | 2009-04-09 | 2016-06-02 | Osseous Technologies Of America | Collagen biomaterial for containment of biomaterials |
US20140163520A1 (en) * | 2009-04-09 | 2014-06-12 | Osseous Technologies Of America | Collagen biomaterial for containment of biomaterials |
US8512397B2 (en) | 2009-04-27 | 2013-08-20 | Sorin Group Italia S.R.L. | Prosthetic vascular conduit |
US8468667B2 (en) | 2009-05-15 | 2013-06-25 | Jenavalve Technology, Inc. | Device for compressing a stent |
US8808369B2 (en) | 2009-10-05 | 2014-08-19 | Mayo Foundation For Medical Education And Research | Minimally invasive aortic valve replacement |
US9050264B2 (en) | 2009-11-07 | 2015-06-09 | University Of Iowa Research Foundation | Cellulose capsules and methods for making them |
US9226826B2 (en) | 2010-02-24 | 2016-01-05 | Medtronic, Inc. | Transcatheter valve structure and methods for valve delivery |
US8652204B2 (en) | 2010-04-01 | 2014-02-18 | 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 |
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 |
US11833041B2 (en) | 2010-04-01 | 2023-12-05 | Medtronic, Inc. | Transcatheter valve with torsion spring fixation and related systems and methods |
US10307251B2 (en) | 2010-05-20 | 2019-06-04 | Jenavalve Technology, Inc. | Catheter system for introducing an expandable stent into the body of a patient |
US9597182B2 (en) | 2010-05-20 | 2017-03-21 | Jenavalve Technology Inc. | Catheter system for introducing an expandable stent into the body of a patient |
US11147669B2 (en) | 2010-05-20 | 2021-10-19 | Jenavalve Technology, Inc. | Catheter system for introducing an expandable stent into the body of a patient |
US11278406B2 (en) | 2010-05-20 | 2022-03-22 | Jenavalve Technology, Inc. | Catheter system for introducing an expandable heart valve stent into the body of a patient, insertion system with a catheter system and medical device for treatment of a heart valve defect |
US10856978B2 (en) | 2010-05-20 | 2020-12-08 | Jenavalve Technology, Inc. | Catheter system |
US9248017B2 (en) | 2010-05-21 | 2016-02-02 | Sorin Group Italia S.R.L. | Support device for valve prostheses and corresponding kit |
US9744031B2 (en) | 2010-05-25 | 2017-08-29 | Jenavalve Technology, Inc. | Prosthetic heart valve and endoprosthesis comprising a prosthetic heart valve and a stent |
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 |
US10603164B2 (en) | 2010-05-25 | 2020-03-31 | Jenavalve Technology, Inc. | Prosthetic heart valve and endoprosthesis comprising a prosthetic heart valve and a stent |
US9918833B2 (en) | 2010-09-01 | 2018-03-20 | Medtronic Vascular Galway | Prosthetic valve support structure |
US11786368B2 (en) | 2010-09-01 | 2023-10-17 | Medtronic Vascular Galway | Prosthetic valve support structure |
US10835376B2 (en) | 2010-09-01 | 2020-11-17 | Medtronic Vascular Galway | Prosthetic valve support structure |
US10201418B2 (en) | 2010-09-10 | 2019-02-12 | Symetis, SA | Valve replacement devices, delivery device for a valve replacement device and method of production of a valve replacement device |
US10869760B2 (en) | 2010-09-10 | 2020-12-22 | Symetis Sa | Valve replacement devices, delivery device for a valve replacement device and method of production of a valve replacement device |
US9289289B2 (en) | 2011-02-14 | 2016-03-22 | Sorin Group Italia S.R.L. | Sutureless anchoring device for cardiac valve prostheses |
US9161836B2 (en) | 2011-02-14 | 2015-10-20 | Sorin Group Italia S.R.L. | Sutureless anchoring device for cardiac valve prostheses |
US8795319B2 (en) | 2011-03-02 | 2014-08-05 | Cook Medical Technologies Llc | Embolization coil |
US11771544B2 (en) | 2011-05-05 | 2023-10-03 | Symetis Sa | Method and apparatus for compressing/loading stent-valves |
US8998976B2 (en) | 2011-07-12 | 2015-04-07 | Boston Scientific Scimed, Inc. | Coupling system for medical devices |
US9668859B2 (en) | 2011-08-05 | 2017-06-06 | California Institute Of Technology | Percutaneous heart valve delivery systems |
US9510947B2 (en) | 2011-10-21 | 2016-12-06 | Jenavalve Technology, Inc. | Catheter system for introducing an expandable heart valve stent into the body of a patient |
US9370421B2 (en) | 2011-12-03 | 2016-06-21 | Boston Scientific Scimed, Inc. | Medical device handle |
US8685084B2 (en) | 2011-12-29 | 2014-04-01 | Sorin Group Italia S.R.L. | Prosthetic vascular conduit and assembly method |
US9138314B2 (en) | 2011-12-29 | 2015-09-22 | Sorin Group Italia S.R.L. | Prosthetic vascular conduit and assembly method |
US10172708B2 (en) | 2012-01-25 | 2019-01-08 | Boston Scientific Scimed, Inc. | Valve assembly with a bioabsorbable gasket and a replaceable valve implant |
US10940167B2 (en) | 2012-02-10 | 2021-03-09 | Cvdevices, Llc | Methods and uses of biological tissues for various stent and other medical applications |
US9878127B2 (en) | 2012-05-16 | 2018-01-30 | Jenavalve Technology, Inc. | Catheter delivery system for heart valve prosthesis |
US11000390B2 (en) | 2012-06-15 | 2021-05-11 | Trivascular, Inc. | Bifurcated endovascular prosthesis having tethered contralateral leg |
US9132025B2 (en) | 2012-06-15 | 2015-09-15 | Trivascular, Inc. | Bifurcated endovascular prosthesis having tethered contralateral leg |
US11779479B2 (en) | 2012-06-15 | 2023-10-10 | Trivascular, Inc. | Bifurcated endovascular prosthesis having tethered contralateral leg |
US10195060B2 (en) | 2012-06-15 | 2019-02-05 | Trivascular, Inc. | Bifurcated endovascular prosthesis having tethered contralateral leg |
US11382739B2 (en) | 2012-06-19 | 2022-07-12 | Boston Scientific Scimed, Inc. | Replacement heart valve |
US10555809B2 (en) | 2012-06-19 | 2020-02-11 | Boston Scientific Scimed, Inc. | Replacement heart valve |
US11406495B2 (en) | 2013-02-11 | 2022-08-09 | Cook Medical Technologies Llc | Expandable support frame and medical device |
US9744037B2 (en) | 2013-03-15 | 2017-08-29 | California Institute Of Technology | Handle mechanism and functionality for repositioning and retrieval of transcatheter heart valves |
US9629718B2 (en) | 2013-05-03 | 2017-04-25 | Medtronic, Inc. | Valve delivery tool |
US10568739B2 (en) | 2013-05-03 | 2020-02-25 | Medtronic, Inc. | Valve delivery tool |
US11793637B2 (en) | 2013-05-03 | 2023-10-24 | Medtronic, Inc. | Valve delivery tool |
US9867694B2 (en) | 2013-08-30 | 2018-01-16 | Jenavalve Technology Inc. | Radially collapsible frame for a prosthetic valve and method for manufacturing such a frame |
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 |
US10433954B2 (en) | 2013-08-30 | 2019-10-08 | Jenavalve Technology, Inc. | Radially collapsible frame for a prosthetic valve and method for manufacturing such a frame |
US9901445B2 (en) | 2014-11-21 | 2018-02-27 | Boston Scientific Scimed, Inc. | Valve locking mechanism |
US10449043B2 (en) | 2015-01-16 | 2019-10-22 | 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 |
US9788942B2 (en) | 2015-02-03 | 2017-10-17 | Boston Scientific Scimed Inc. | Prosthetic heart valve having tubular seal |
US10201417B2 (en) | 2015-02-03 | 2019-02-12 | Boston Scientific Scimed Inc. | Prosthetic heart valve having tubular seal |
US10285809B2 (en) | 2015-03-06 | 2019-05-14 | Boston Scientific Scimed Inc. | TAVI anchoring assist device |
US10426617B2 (en) | 2015-03-06 | 2019-10-01 | Boston Scientific Scimed, Inc. | Low profile valve locking mechanism and commissure assembly |
US10080652B2 (en) | 2015-03-13 | 2018-09-25 | Boston Scientific Scimed, Inc. | Prosthetic heart valve having an improved tubular seal |
US11065113B2 (en) | 2015-03-13 | 2021-07-20 | Boston Scientific Scimed, Inc. | Prosthetic heart valve having an improved tubular seal |
US10709555B2 (en) | 2015-05-01 | 2020-07-14 | Jenavalve Technology, Inc. | Device and method with reduced pacemaker rate in heart valve replacement |
US11337800B2 (en) | 2015-05-01 | 2022-05-24 | Jenavalve Technology, Inc. | Device and method with reduced pacemaker rate in heart valve replacement |
US11730595B2 (en) | 2015-07-02 | 2023-08-22 | Boston Scientific Scimed, Inc. | Adjustable nosecone |
US10195392B2 (en) | 2015-07-02 | 2019-02-05 | Boston Scientific Scimed, Inc. | Clip-on catheter |
US10335277B2 (en) | 2015-07-02 | 2019-07-02 | Boston Scientific Scimed Inc. | Adjustable nosecone |
US10856973B2 (en) | 2015-08-12 | 2020-12-08 | Boston Scientific Scimed, Inc. | Replacement heart valve implant |
US10136991B2 (en) | 2015-08-12 | 2018-11-27 | Boston Scientific Scimed Inc. | Replacement heart valve implant |
US10179041B2 (en) | 2015-08-12 | 2019-01-15 | Boston Scientific Scimed Icn. | Pinless release mechanism |
US11684476B2 (en) | 2015-12-03 | 2023-06-27 | Medtronic Vascular, Inc. | Venous valve prostheses |
US20170156863A1 (en) * | 2015-12-03 | 2017-06-08 | Medtronic Vascular, Inc. | Venous valve prostheses |
US10143554B2 (en) * | 2015-12-03 | 2018-12-04 | Medtronic Vascular, Inc. | Venous valve prostheses |
US10973640B2 (en) | 2015-12-03 | 2021-04-13 | Medtronic Vascular, Inc. | Venous valve prostheses |
US10342660B2 (en) | 2016-02-02 | 2019-07-09 | Boston Scientific Inc. | Tensioned sheathing aids |
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 |
US11382742B2 (en) | 2016-05-13 | 2022-07-12 | Boston Scientific Scimed, Inc. | Medical device handle |
US10583005B2 (en) | 2016-05-13 | 2020-03-10 | Boston Scientific Scimed, Inc. | Medical device handle |
US10709552B2 (en) | 2016-05-16 | 2020-07-14 | Boston Scientific Scimed, Inc. | Replacement heart valve implant with invertible leaflets |
US20170325938A1 (en) | 2016-05-16 | 2017-11-16 | Boston Scientific Scimed, Inc. | Replacement heart valve implant with invertible leaflets |
US10201416B2 (en) | 2016-05-16 | 2019-02-12 | Boston Scientific Scimed, Inc. | Replacement heart valve implant with invertible leaflets |
US11197754B2 (en) | 2017-01-27 | 2021-12-14 | Jenavalve Technology, Inc. | Heart valve mimicry |
US10828154B2 (en) | 2017-06-08 | 2020-11-10 | Boston Scientific Scimed, Inc. | Heart valve implant commissure support structure |
US10898325B2 (en) | 2017-08-01 | 2021-01-26 | Boston Scientific Scimed, Inc. | Medical implant locking mechanism |
US10939996B2 (en) | 2017-08-16 | 2021-03-09 | Boston Scientific Scimed, Inc. | Replacement heart valve commissure assembly |
US11246625B2 (en) | 2018-01-19 | 2022-02-15 | Boston Scientific Scimed, Inc. | Medical device delivery system with feedback loop |
US11191641B2 (en) | 2018-01-19 | 2021-12-07 | Boston Scientific Scimed, Inc. | Inductance mode deployment sensors for transcatheter valve system |
US11147668B2 (en) | 2018-02-07 | 2021-10-19 | Boston Scientific Scimed, Inc. | Medical device delivery system with alignment feature |
US11439732B2 (en) | 2018-02-26 | 2022-09-13 | Boston Scientific Scimed, Inc. | Embedded radiopaque marker in adaptive seal |
US11229517B2 (en) | 2018-05-15 | 2022-01-25 | Boston Scientific Scimed, Inc. | Replacement heart valve commissure assembly |
US11504231B2 (en) | 2018-05-23 | 2022-11-22 | Corcym S.R.L. | Cardiac valve prosthesis |
US11241310B2 (en) | 2018-06-13 | 2022-02-08 | Boston Scientific Scimed, Inc. | Replacement heart valve delivery device |
US11241312B2 (en) | 2018-12-10 | 2022-02-08 | Boston Scientific Scimed, Inc. | Medical device delivery system including a resistance member |
US11439504B2 (en) | 2019-05-10 | 2022-09-13 | Boston Scientific Scimed, Inc. | Replacement heart valve with improved cusp washout and reduced loading |
US11826490B1 (en) | 2020-12-29 | 2023-11-28 | Acell, Inc. | Extracellular matrix sheet devices with improved mechanical properties and method of making |
US11969341B2 (en) | 2022-11-18 | 2024-04-30 | Corcym S.R.L. | Cardiac valve prosthesis |
Also Published As
Publication number | Publication date |
---|---|
US8444687B2 (en) | 2013-05-21 |
US20010039450A1 (en) | 2001-11-08 |
US20090048662A1 (en) | 2009-02-19 |
US8613763B2 (en) | 2013-12-24 |
US20060142846A1 (en) | 2006-06-29 |
US7597710B2 (en) | 2009-10-06 |
US20040210301A1 (en) | 2004-10-21 |
US20090157169A1 (en) | 2009-06-18 |
US7452371B2 (en) | 2008-11-18 |
US7520894B2 (en) | 2009-04-21 |
Similar Documents
Publication | Publication Date | Title |
---|---|---|
US7918882B2 (en) | Implantable vascular device comprising a bioabsorbable frame | |
US7520894B2 (en) | Implantable vascular device | |
US9078746B2 (en) | Implantable vascular device | |
EP2517674B1 (en) | Implantable vascular device | |
US8382822B2 (en) | Implantable vascular device | |
CA2494970C (en) | Stent and method of forming a stent with integral barbs | |
AU2001238038A1 (en) | Implantable vascular device | |
US20120222969A1 (en) | Stent and method of forming a stent with integral barbs |
Legal Events
Date | Code | Title | Description |
---|---|---|---|
AS | Assignment |
Owner name: OREGON HEALTH AND SCIENCE UNIVERSITY, OREGON Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:PAVCNIK, DUSAN;KELLER, FREDERICK S.;ROSCH, JOSEF;REEL/FRAME:015695/0320 Effective date: 20041027 Owner name: COOK BIOTECH INCORPORATED, INDIANA Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNOR:OBERMILLER, JOSEPH W.;REEL/FRAME:015695/0288 Effective date: 20041027 Owner name: COOK INCORPORATED, INDIANA Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNORS:OSBORNE, THOMAS A.;DEFORD, JOHN A.;ROBERTS, JOSEPH W.;AND OTHERS;REEL/FRAME:015695/0368;SIGNING DATES FROM 20041026 TO 20050211 |
|
STCB | Information on status: application discontinuation |
Free format text: ABANDONED -- FAILURE TO RESPOND TO AN OFFICE ACTION |