A stent is disclosed, which includes a stent body (2) and a single-radiopaque component (1) disposed at one or each of a proximal end and a distal end of the stent body (2). The stent body (2) is composed of rings and struts, and one part of the single-radiopaque component (1) is received in a receptacle (3) of the stent body (2) and another part of the single-radiopaque component (1) protrudes out of a surface of the stent body (2). The area of the protruding part (11) of the single-radiopaque component (1) is larger than an area of the embedded part (10), the presence of the protruding part (11) allowing the single-radiopaque component (1) to appear wider and thicker in a radiologic image, enhancing the radiopacity of the stent during surgery.

A stent includes a tubular body formed of one or more interwoven wires, the tubular body having first and second opposing open ends and a lumen extending therebetween. The stent further includes a first anchor member disposed adjacent the first open end and a second anchor member disposed adjacent the second open end, the first and second anchor members each extending radially outward from the tubular body, the first and second anchor members each having an outer diameter larger than an outer diameter of the tubular body disposed between the first and second anchor members. A plurality of spacer members are disposed around the first open end and extending longitudinally beyond the first open end, wherein when a pulling force is applied to the spacer members, the outer diameter of the tubular body is not reduced.

A prosthetic device for treating a native valve of a heart includes a sealing element and an anchoring element. The sealing element comprises a braided mesh material. The sealing element is dimensioned to be deployed at the native valve. The sealing element is configured to both be radially expanded and radially reduced while at a position between the native valve leaflets. The anchoring element is coupled to the sealing element and is configured to support the sealing element between the native valve leaflets.

Disclosed herein are embodiments of a reinforced collagen matrix device for superior capsule repair. The device can include a collagen matrix cover, a first reinforcement strip positioned along the first side of the cover, and a second reinforcement strip positioned along the second side of the cover. A first end and a second end of the first and second reinforcement strips can extend past the first end and the second end of the collagen matrix cover so as not be covered by the collagen matrix cover. The collagen matrix cover can be folded along a first fold and a second fold and extend over the first and second reinforcement strips so that a portion of the first and second reinforcement strips are covered by the collagen matrix cover along a portion of the length of the first reinforcement strip.

This shoulder prosthesis glenoid component (2) has on one of its faces an articulation surface (S.sub.A) adapted to cooperate with a humeral head and having, on an opposite face (S.sub.G) adapted to be immobilized on the glenoid cavity (G) of a shoulder, a keel (4) for anchoring it in the glenoid cavity (G). This keel (4) comprises a body (5) that extends from the opposite face (S.sub.G). The keel (4) comprises at least one fin (6) projecting from the body (5) 2 which runs over at least a part of the perimeter of the body (5).

An exemplary implantable prosthetic device has a coaption element and at least one anchor. The coaption element is configured to be positioned within the native heart valve orifice to help fill a space where the native valve is regurgitant and form a more effective seal. The coaption element can have a structure that is impervious to blood and that allows the native leaflets to close around the coaption element during ventricular systole to block blood from flowing from the left or right ventricle back into the left or right atrium, respectively. The coaption element can be connected to leaflets of the native valve by the anchor.

Prosthetic heart valves may be delivered to a targeted native heart valve site via one or more delivery catheters. In some embodiments, the prosthetic heart valve includes structural features that securely anchor the prosthetic heart valve to the anatomy at the site of the native heart valve. Such structural features can provide robust migration resistance. In addition, the prosthetic heart valves can include structural features that improve sealing between the prosthetic valve and native valve anatomy to mitigate paravalvular leakage. In particular implementations, the prosthetic heart valves occupy a small delivery profile, thereby facilitating a smaller delivery catheter system for advancement to the heart. Some delivery catheter systems can include a curved inner catheter to facilitate deployment of the prosthetic heart valve to a native tricuspid valve site via a superior vena cava or inferior vena cava.

A docking device for docking a prosthetic valve at a native valve of a heart includes a coiled body and a high friction sleeve. The coiled body has an upper region, a central region, and a lower region. The docking device is configured to be implanted at the native valve with the upper region positioned in a first chamber of the heart, the lower region positioned in a second chamber of the heart, and the central region positioned to extend around a plurality of leaflets of the native valve. A high friction sleeve covers at least a portion of the central region. The high friction sleeve comprises a material configured to generate more friction between the prosthetic valve and the docking device than an exterior surface of the coiled body.

An implantable vein frame is contemplated in which two ring members are rigidly joined in spaced axial alignment via one or more interconnecting members. One of the one or more interconnecting members defines a protruding region that acts upon the implant placed within the frame and/or the vein that the vein frame is placed within to define a sinus region. The implant is placed within and scaffolded by the vein frame, and the vein frame is subsequently inserted within a vein via a venotomy, or interposed between two vein segments via vein interposition graft. The vein frame acts to support the structural integrity of the implant, and to scaffold and anchor the implant in place with the vein.

A joining arrangement between a main tube and a side arm (5) in a side arm stent graft (1). The side arm (5) is stitched into an aperture (11) in the main tube and is in fluid communication with it. The aperture is triangular, elliptical or rectangular and the side arm is cut off at an angle to leave an end portion having a circumferential length equal to the circumference of the aperture. The side arm can also include a connection socket (76) comprising a first resilient ring (79) around the arm at its end, a second resilient ring (80) spaced apart along the arm from the first ring and a zig zag resilient stent (82) between the first and second rings. The zig-zag resilient stent can be a compression stent. Both the main tube and the side arm are formed from seamless tubular biocompatible graft material.