Abstract: The present invention provides a prosthetic heart valve, including a stent, prosthetic leaflets and an occlusion mechanism. Both the prosthetic leaflets and the occlusion mechanism are connected to the stent. The occlusion mechanism is able to extend outwards away from the stent and fill up a recessed portion of a native valve annulus, thereby closely fitting the prosthetic heart valve against the native valve annulus and effectively preventing paravalvular leakage.

Abstract: An artificial heart valve (100), comprising a body stent and an artificial valve leaflet (130), wherein an outflow end of the body stent is connected to an inflow end of the artificial valve leaflet (130), and when the artificial heart valve (100) is implanted in the heart, the body stent is secured to a mitral valve annulus, and the artificial valve leaflet (130) is in sealing contact with an inner side of a native posterior leaflet (21) of a mitral valve leaflet and mates with a native anterior leaflet (22) of the mitral valve leaflet, so as to ensure unidirectional flow of blood in a left atrium (10) and a left ventricle (20). The artificial valve leaflet (130) is used for space occupation and mating, thereby effectively utilizing the healthy native anterior leaflet (22), and improving the mating performance and service life of the valve leaflet.

Abstract: A delivery catheter, comprising a first catheter section (10), a second catheter section (20), a first pull wire assembly (30) and a second pull wire assembly (40); wherein the first pull wire assembly (30) comprises a first pull wire (32) and a first pull wire ring (31), when the first pull wire (32) is pulled, the first pull wire ring (31) drives the first catheter section (10) to bend; the second pull wire assembly (40) comprises a second pull wire (42) and a second pull wire ring (41), wherein the second pull wire ring (41) is disposed at a distal end of the second catheter section (20) and connected to a proximal end of the first catheter section (10); when the second pull wire (42) is pulled, the second pull wire ring (41) drives the second catheter section (20) to bend; an angle at which the first catheter section (10) can bend is greater than an angle at which the second catheter section (20) can bend.

Abstract: An anchoring device (100, 200, 300) for prosthetic heart valve (400) and a prosthetic heart valve system. The prosthetic heart valve system includes an anchoring device (100, 200, 300) and a prosthetic heart valve (400). The anchoring device (100, 200, 300) includes an anchoring section (110, 210, 310) and a supporting section (120, 220, 320) that are axially connected to each other. The anchoring section (110, 210, 310) has an annular first cavity (111, 211, 311) configured to accommodate a prosthetic heart valve (400). The supporting section (120, 220, 320) is arranged on one side of the anchoring section (110, 210, 310) along the axial direction thereof. The supporting section (120, 220, 320) includes at least two elastic wires (121, 221, 321) arranged sequentially on the circumference of the anchoring section (110, 210, 310).

Abstract: A catheter assembly (1), an implant system, an implant delivery system and a method of use thereof. In the implant delivery system, an inner tube (120) is made of an elastic material, and an outer sheath tube (110) and a guidewire tube (130) are each made of a plastic material. A distal end portion of each of the outer sheath tube (110) and the guidewire tube (130) is shaped into a curved form to provide a curved channel for the inner tube (120). The inner tube (120) is elastically inserted through the curved channel. This dispenses with the need for bending control from an outer sheath tube control device (21) and an inner tube control device (22), reducing requirements and difficulties in designing them and thus resulting in cost savings. Moreover, it makes the implant delivery system more easily operable, safer and more reliable, with lower requirements on a surgical incision, and capable of delivering a stent through a curved access accurately to a designated site.

Abstract: An implant delivery device and an implant delivery system. The implant delivery device is applied to a catheter assembly (70) including a first inner tube (71) and a second inner tube (72). The implant delivery device includes two power conversion assemblies (10) which are sequentially arranged in the direction of a baseline (H), each of which includes a master member (11) and a slave member (12) in engagement with the master member (11). The slave member (12) of one of the two power conversion assemblies (10) is adapted for connection with the first inner tube (71), and the slave member (12) of the other of the two power conversion assemblies (10) is adapted for connection with the second inner tube (72). The power conversion assemblies (10) are configured to convert a rotational motion of the master members (11) to a linear motion of the slave members (12) in the direction of the baseline (H).

Abstract: A brazing joint, a brazing method, and a device for promoting solder rheology and gas overflow are provided. The brazing joint includes a first base metal, a second base metal, and a brazing seam located therebetween. The brazing seam is formed by filling a solder in a gap formed by welding surfaces of the first and the second base metal and melting it to connect the first and the second base metal. The brazing seam is a concave-shaped brazing seam. The gap defines a first distance and a second distance, the first distance is located at an edge of the gap, the second distance is located at the edge or an inside of the gap, the first distance is greater than the second distance, and a curved surface is formed between the location of the first distance and the location of the second distance for transition.

Abstract: An implant delivery handle, an implant system, a delivery system and a method of use thereof are disclosed. Transmission systems in the implant delivery handle each include a lead screw, an inner tube coupling member, an outer gear and an inner gear. The outer gear rotatably engages the inner gear and is configured to drive rotation of the inner gear. The lead screw is coupled to a first inner tube (11) or a second inner tube (12) through the inner tube coupling member. The lead screw also engages the inner gear and rotates therewith to cause axial movement of the first inner tube (11) or the second inner tube (12). A transmission ratio of the outer gear to the inner gear is greater than 1.

Abstract: An active bipolar cardiac electrical is assembled by coupling an inner conductor coil to a connector pin to form an inner conductor assembly. The inner conductor assembly is threaded through a connector insulator. An insulating tubing is placed over the inner coil. A proximal end of the insulating tubing is sleeved over the distal extension of the connector insulator. An outer conductor coil is coupled to a ring connector to form an outer conductor assembly. The inner conductor assembly is threaded through the outer conductor assembly. The ring connector is sleeved on the distal extension of the connector insulator and over the insulator tubing. A proximal seal is sleeved over a socket end of the connector pin. The proximal seal is seated on the proximal extension of the connector insulator.

Abstract: A passive cardiac electrical lead is assembled by coupling an inner conductor coil to a connector pin to form an inner conductor assembly. The inner conductor assembly is threaded through a connector insulator. An insulator tubing is placed over the inner coil. A proximal end of the insulator tubing is sleeved over the distal extension of the connector insulator. An outer conductor coil is coupled to a ring connector to form an outer conductor assembly. The inner conductor assembly is threaded through the outer conductor assembly. The ring connector is sleeved on the distal extension of the connector insulator and over the insulator tubing. A proximal seal is sleeved over a socket end of the connector pin. A portion of the proximal seal is seated on the proximal extension of the connector insulator.

Abstract: An active bipolar cardiac electrical is assembled by coupling an inner conductor coil to a connector pin to form an inner conductor assembly. The inner conductor assembly is threaded through a connector insulator. An insulating tubing is placed over the inner coil. A proximal end of the insulating tubing is sleeved over the distal extension of the connector insulator. An outer conductor coil is coupled to a ring connector to form an outer conductor assembly. The inner conductor assembly is threaded through the outer conductor assembly. The ring connector is sleeved on the distal extension of the connector insulator and over the insulator tubing. A proximal seal is sleeved over a socket end of the connector pin. The proximal seal is seated on the proximal extension of the connector insulator.

Abstract: A passive cardiac electrical lead is assembled by coupling an inner conductor coil to a connector pin to form an inner conductor assembly. The inner conductor assembly is threaded through a connector insulator. An insulator tubing is placed over the inner coil. A proximal end of the insulator tubing is sleeved over the distal extension of the connector insulator. An outer conductor coil is coupled to a ring connector to form an outer conductor assembly. The inner conductor assembly is threaded through the outer conductor assembly. The ring connector is sleeved on the distal extension of the connector insulator and over the insulator tubing. A proximal seal is sleeved over a socket end of the connector pin. A portion of the proximal seal is seated on the proximal extension of the connector insulator.