CN212490258U - Suture locking and cutting device and suture locking and cutting system - Google Patents

Abstract

The utility model provides a pair of suture locking cutting device, include: the implant comprises a winding assembly and a tangent assembly, the winding assembly is provided with a first through hole for threading the suture, the tangent assembly comprises a blade, and the blade faces the suture passing through the first through hole; the conveying assembly comprises a tangent driving shaft and a winding driving piece movably arranged in the tangent driving shaft in a penetrating mode, and the far end of the winding driving piece is detachably connected with the winding assembly to drive the winding assembly to rotate so that the suture can be wound on the outer peripheral face of the winding assembly; the distal end of the tangent drive shaft is removably attached to the tangent assembly to move the blade toward the suture and sever the suture. The utility model provides a suture locking cutting device and suture locking cutting system are strong, little, the fracture risk of suture lower to the damage of suture to the locking force of suture.

Description

Suture locking and cutting device and suture locking and cutting system

Technical Field

The utility model belongs to the field of medical equipment, a valve intervention treatment apparatus is related to, in particular to suture locking and cutting device and suture locking and cutting system.

Background

Mitral insufficiency is one of the most common valvular lesions at present, and surgical open mitral valvuloplasty and artificial valve replacement are the most effective methods for treating mitral insufficiency, but the surgical operation requires extracorporeal circulation technical support, so that the trauma is large, the complications are more, and the death rate is high.

Percutaneous mitral valve intervention repair techniques are safer mitral valve repair methods, represented by transcatheter annuloplasty. In the prior art, a plurality of anchors with sutures are respectively anchored on a heart valve annulus along the circumferential direction of the valve annulus, then the mitral valve annulus is shrunk by tightening the sutures, the tightened sutures are locked by an intervention type locking device, and then redundant sutures are cut by a suture cutting device.

The prior art discloses an intervention type locking device, which is characterized in that a thread penetrates through a titanium nail, then the titanium nail is crushed by external force to deform the titanium nail, a suture is fixed by friction force generated between an indentation of the titanium nail and the suture, and the friction force is small and the locking force is weak because the contact area between the indentation and the suture is small; moreover, after the implantation, repeated friction between the indentation and the suture can cause suture damage under the condition of continuous beating of the heart, and the risk of suture fracture is high.

SUMMERY OF THE UTILITY MODEL

The utility model provides a locking force to the suture is strong, little, the lower suture locking cutting device of fracture risk of suture and suture locking cutting system to the damage of suture.

In a first aspect, the present invention provides a suture locking and cutting device, including:

the implant comprises a winding assembly and a tangent assembly, the winding assembly is provided with a first through hole for threading the suture, the tangent assembly comprises a blade, and the blade faces the suture passing through the first through hole; and

the conveying assembly comprises a tangent driving shaft and a winding driving piece movably arranged in the tangent driving shaft in a penetrating mode, and the far end of the winding driving piece is detachably connected with the winding assembly so as to drive the winding assembly to rotate and enable the suture to be wound on the outer peripheral face of the winding assembly; the distal end of the tangent drive shaft is removably attached to the tangent assembly to move the blade toward the suture and sever the suture.

On the other hand, the suture locking cutting system that this application provided, reach including guiding device suture locking cutting device, guiding device includes the sheath pipe and connects the accent of sheath pipe near-end is bent the handle, wire winding driving piece and tangent line driving shaft wear adorn in among the guiding device, control the handle and be located outside the near-end of accent bent handle, the distal end of carrying the subassembly is located outside the distal end of sheath pipe and butt the sheath pipe.

The utility model provides a suture locking and cutting device and a suture locking and cutting system, which can wind and lock the suture by driving the winding component to rotate, and at the moment, the suture can be locked by friction for the first time; in the process of driving the thread cutting assembly to gradually approach the suture, the suture can be compressed for the second time through friction force, the locking force of the suture can be improved through double friction force, and the suture is cut off synchronously in the process of compressing the suture for the second time. Therefore, the suture locking and cutting device provided by the utility model avoids long-term friction of the deformed lock catch indentation, and reduces the damage to the suture; the suture is locked by two different friction forces, so that the locking force is higher; meanwhile, the two processes of locking the suture and cutting the suture can be simultaneously realized through one device and one step, a locking device and a thread cutting device are not required to be independently used, the function diversification and the structure compactness of the device are greatly improved, the operation time is shortened, and the operation risk is reduced.

Drawings

In order to more clearly illustrate the technical solutions of the embodiments of the present invention, the drawings needed to be used in the embodiments will be briefly described below, and it is obvious that the drawings in the following description are only some embodiments of the present invention, and it is obvious for those skilled in the art that other drawings can be obtained according to these drawings without creative efforts.

Fig. 1 is a schematic structural diagram of a suture locking and cutting system provided by an embodiment of the present invention;

FIG. 2 is a schematic structural view of the suture locking and cutting device provided in FIG. 1;

FIG. 3 is a schematic illustration of the implant provided in FIG. 1 with the suture left in the heart;

FIG. 4 is a schematic structural view of the guide apparatus provided in FIG. 1;

FIG. 5 is a schematic structural view of the delivery assembly provided in FIG. 2;

FIG. 6 is a partial axial cross-sectional view of the delivery assembly provided in FIG. 5;

FIG. 7a is a schematic view of the rotary joint provided in FIG. 5 from a first perspective;

FIG. 7b is a schematic structural view of the rotational connection provided in FIG. 5 from a second perspective;

FIG. 7c is a schematic structural view of a third perspective of the rotational coupling provided in FIG. 5;

FIG. 8a is a cross-sectional view of a portion of the suture locking cutting device provided in FIG. 2;

FIG. 8b is a cross-sectional view of the implant provided in FIG. 8a prior to threading a thread;

FIG. 9a is a schematic view of the pawl shown in FIG. 5 from a first perspective;

FIG. 9b is a cross-sectional view of the jaw provided in FIG. 9a, taken along the axial direction;

FIG. 9c is a schematic diagram of the pawl provided in FIG. 5 from a second perspective;

FIG. 10 is a schematic view of the suture locking and severing device provided in FIG. 2, shown in disassembled configuration;

FIG. 11 is a schematic view of the suture locking cutting device provided in FIG. 2 with a portion of the housing broken away;

FIG. 12 is a schematic view of the suture locking cutting device provided in FIG. 2 with the housing removed;

FIG. 13a is a schematic structural view of the housing provided in FIG. 10 from a first perspective;

FIG. 13b is a schematic structural view of the enclosure provided in FIG. 10 from a second perspective;

FIG. 13c is a schematic structural view of the enclosure provided in FIG. 10 from a third perspective;

FIG. 13d is a schematic diagram of a fourth perspective of the housing provided in FIG. 10;

FIG. 13e is a cross-sectional view of the housing provided in FIG. 10;

FIG. 13f is another cross-sectional view of the enclosure provided in FIG. 10;

FIG. 14a is a schematic structural view of the first stop assembly provided in FIG. 10;

FIG. 14b is a structurally exploded view of the first stop assembly provided in FIG. 14 a;

FIG. 14c is a schematic structural view of the first support provided in FIG. 14 a;

FIG. 15 is a schematic structural view of the rotating assembly provided in FIG. 10;

FIG. 16a is a schematic view of the structure of the rotatable wheel provided in FIG. 10 from a first perspective;

FIG. 16b is a cross-sectional view of the rotatable wheel provided in FIG. 16 a;

FIG. 16c is a schematic structural view of the rotatable wheel provided in FIG. 10 from a second perspective;

FIG. 17a is a schematic view of the rotating assembly provided in FIG. 10 from a first perspective;

FIG. 17b is a cross-sectional view of the rotating assembly provided in FIG. 17 a;

FIG. 17c is a schematic view of the rotating assembly provided in FIG. 10 from a second perspective;

FIG. 18a is a schematic view of the tangent line assembly provided in FIG. 10 from a first perspective;

FIG. 18b is a schematic diagram of a second perspective view of the tangent line assembly provided in FIG. 10;

FIG. 19a is a schematic view of the structure of the first view of the moving assembly provided in FIG. 10;

FIG. 19b is a schematic structural view of a second perspective of the movement assembly provided in FIG. 10;

FIG. 19c is a cross-sectional view of the moving assembly provided in FIG. 19 b;

FIG. 19d is a schematic structural view of a third perspective of the moving assembly provided in FIG. 10;

FIG. 20a is a schematic structural view of the wire winding assembly provided in FIG. 10;

FIG. 20b is a schematic view of the wire winding assembly provided in FIG. 10, shown in a disassembled configuration;

FIG. 20c is a schematic view of the second ratchet wheel provided in FIG. 20 b;

fig. 20d is a structural schematic view from a first perspective of the bobbin provided in fig. 20 b;

fig. 20e is a structural schematic view from a second perspective of the bobbin provided in fig. 20 b;

FIG. 20f is a cross-sectional view of the bobbin provided in FIG. 20 e;

FIG. 21 is a schematic structural view of the second stop assembly provided in FIG. 10;

FIG. 22a is a schematic structural view of the base provided in FIG. 10;

FIG. 22b is a schematic view of the base and the second position-limiting assembly shown in FIG. 10 at a first viewing angle;

FIG. 22c is a schematic structural view of the base and the second position-limiting assembly shown in FIG. 10 at a second viewing angle;

FIG. 23a is an axial cross-sectional view of the implant provided in FIG. 2 prior to threading of the suture and winding of the wire;

FIG. 23b is a radial cross-sectional view of the implant provided in FIG. 2 prior to threading of the suture and winding of the wire;

FIG. 24a is a schematic view of the implant provided in FIG. 2 after the wire has been wound and the shell has been removed;

FIG. 24b is a cross-sectional view of the implant provided in FIG. 2 in an axial direction after being wound;

FIG. 24c is a radial cross-sectional view of the implant provided in FIG. 2 after winding;

FIG. 25 is a cross-sectional view of the implant provided in FIG. 2 taken tangentially in an axial direction;

FIG. 26 is a cross-sectional view of the suture-removed implant provided in FIG. 2, taken tangentially in the axial direction;

FIG. 27 is a schematic view of a plurality of anchors implanted in the mitral annulus by means of sutures;

FIG. 28 is a schematic view of the structure of the transcatheter lockwire cutting device reaching the vicinity of the mitral valve and threading a suture;

FIG. 29 is a schematic view of a suture with a shim secured to the mitral annulus;

FIG. 30 is a schematic view of a suture threaded implant with a spacer;

FIG. 31 is a schematic view of the suture with the spacer being severed by the implant and suture remaining in the heart.

Detailed Description

The technical solution of the embodiments of the present invention will be clearly and completely described below with reference to the accompanying drawings in the embodiments of the present invention.

In the interventional surgical instrument, an end of the interventional surgical instrument close to the operator is defined as a proximal end, and an end of the interventional surgical instrument far from the operator is defined as a distal end. In the drawings of the present invention, the side where N is located is referred to as the proximal end, and the side where M is located is referred to as the distal end. The distal to proximal direction is axial.

The embodiment of the utility model provides a suture locking cutting-off system. The utility model provides a suture locking system of cutting off is applicable to intervention formula heart valve repair process. Specific interventional heart valve repair procedures include, but are not limited to, mitral valve annuloplasty, specifically: anchoring a plurality of anchors connected by sutures to the mitral annulus of the heart, passing a suture locking and severing system through the sutures and into proximity to the mitral valve, tightening the sutures by manipulating the suture locking and severing system to reduce the mitral annulus and sever excess sutures when the mitral annulus is reduced to an appropriate length; after cutting, the implant is left with sutures in the heart to repair the mitral valve. The suture locking and cutting system provided by the utility model can also be used for other intervention type mitral valve or tricuspid valve repair operations.

The following provides an example of the specific structure of the suture locking and cutting system provided by the present application with reference to the accompanying drawings.

Referring to fig. 1, a suture locking and cutting system 1000 provided by the embodiment of the present application includes at least a suture locking and cutting device 100 and a guiding device 300.

Referring to FIG. 2, suture locking and severing device 100 includes at least implant 10, delivery assembly 20, and a steering handle 125 coupled to a proximal end of delivery assembly 20.

Referring to fig. 3, implant 10 is used to implant near the mitral valve and lock suture 200 and sever suture 200 under the action of delivery assembly 20.

Referring to fig. 2 and 3, delivery assembly 20 is removably coupled to implant 10. The delivery assembly 20 is used to deliver the implant 10 to the mitral valve annulus 2000 along the sutures 200 and to control the implant 10 to lock the sutures 200 and sever the sutures 200. After the implant 10 severs the suture 200, the delivery assembly 20 can be separated from the implant 10.

During locking of suture 200, implant 10 is removably threaded onto suture 200 to adjust the length of suture 200 under the influence of delivery assembly 20. When the length of the sutures 200 is adjusted to the appropriate size, the implant 10 cuts through the excess sutures 200 and locks the sutures 200 to maintain the proper shape of the mitral valve annulus 2000, thereby allowing the heart mitral valve annulus 2000 to maintain proper operation. The material of the suture 200 includes, but is not limited to, PTFE, e-PTFE or PET.

Referring to fig. 4, the guiding device 300 includes a sheath 113 and a bending handle 123 connected to the proximal end of the sheath 113. Referring to fig. 1, the suture locking and cutting device 100 is threaded into a guide device 300. the guide device 300 can guide the motion trajectory of the suture locking and cutting device 100, thereby delivering the implant 10 to the mitral annulus 2000 of the heart of a patient.

The following description will be made with reference to the accompanying drawings for illustrating a specific structure of the guide device 300 provided in the present application.

Optionally, referring to fig. 4, the sheath 113 may be a hollow sheath with a bendable or steerable distal end, such as an adjustable bending sheath or a shaping sheath. In this embodiment, the sheath 113 is an adjustable sheath. Specifically, the sheath 113 extends linearly without receiving a bending force, and is bent when receiving a bending force. The sheath 113 is a multi-layer composite hollow tube. A traction ring (not shown) is embedded in the distal end of the sheath tube 113, a traction wire (not shown) is arranged in the tube wall of the sheath tube 113, the distal end of the traction wire is fixedly connected with the traction ring, and the proximal end of the traction wire extends towards the proximal end of the tube body of the sheath tube 113 and is connected with the bending adjusting knob 124.

Bend adjustment handle 123 may be attached to the proximal end of sheath 113. The bending adjustment knob 124 is disposed on the surface, inside or outside of the bending adjustment handle 123. The operator drives the traction wire to move along the axial direction of the sheath tube 113 by controlling the movement of the bending adjusting knob 124, so as to pull the sheath tube 113 to bend or restore to be straight.

The specific structure of the delivery assembly 20 provided herein is illustrated below with reference to the accompanying drawings.

Referring to fig. 5, the conveyor assembly 20 includes a tangent drive shaft 102, a wire winding drive 105, and a pawl 103. The wire winding driving member 105 includes a wire winding driving shaft 101 and a rotary coupling member 104.

Referring to fig. 5, the tangent driving shaft 102 and the winding driving shaft 101 are hollow tubes, and the distal ends thereof are respectively provided with a flexible section with a certain length, so as to be able to bend and transmit torque.

Referring to fig. 5 and 6, the winding driving shaft 101 is movably inserted into the tangent driving shaft 102 and is in clearance fit with the tangent driving shaft 102 to ensure that there is no interference between the winding driving shaft 101 and the tangent driving shaft 102 during relative rotation. Referring to fig. 5, the proximal end of the wire drive shaft 101 extends beyond the proximal end of the tangent drive shaft 102 and is coupled to the steering handle 125 such that the steering handle 125 steers the movement of the wire drive shaft 101. Referring to fig. 6, the distal end of the wound drive shaft 101 extends beyond the distal end of the tangent drive shaft 102 and is connected to the rotating link 104. The rotational connector 104 abuts the implant 10.

Referring to fig. 7a to 7c, the rotating connector 104 includes a first boss 118, a middle protrusion 121 and a second boss 119 which are integrally connected. The middle protrusion 121 is a cylindrical section. The second boss 119 is located at the proximal end of the intermediate tab 121 and the first boss 118 is located at the distal end of the intermediate tab 121. The first boss 118 is adapted to interface with the implant 10.

Referring to fig. 6, the second boss 119 is engaged with the distal end of the winding drive shaft 101. Specifically, the second boss 119 is inserted into the shaft hole of the winding drive shaft 101 and coupled to the distal end of the winding drive shaft 101 to restrict relative rotation between the winding drive shaft 101 and the rotary joint 104. In the present invention, the shaft hole of the component is a through hole located at the approximate central axis of the component and extending along the axial direction.

Referring to fig. 7a, the second boss 119 may be a square block or a cylindrical block. The radial dimension of the second boss 119 in a certain direction is smaller than the outer diameter dimension of the intermediate protrusion 121, and a first step surface 120 is formed between the second boss 119 and the intermediate protrusion 121.

Referring to fig. 8a and 8b, the outer diameter of the middle protrusion 121 is larger than the inner diameter of the tangent driving shaft 102, so that the winding driving shaft 101 and the tangent driving shaft 102 abut against the first step surface 120 to limit the winding driving shaft 101 from moving proximally relative to the tangent driving shaft 102. Since the distal portion (first boss 118) of the rotational connector 104 abuts the implant 10, axial rotation of the wire-wound drive shaft 101 causes rotation of the rotational connector 104 and, thus, the implant 10.

Alternatively, the wound drive shaft 101 and the rotation link 104 are both made of SUS304, and the connection between the wound drive shaft 101 and the rotation link 104 is preferably laser welded.

Referring to fig. 5 and 6, the tangential driving shaft 102 has a certain axial length and is inserted into the sheath 113. The proximal end of the tangential drive shaft 102 is connected to the distal end of the steering handle 125 (as shown in fig. 3), and the distal end of the tangential drive shaft 102 extends from the distal end of the sheath 113. The distal end of the tangent drive shaft 102 is provided with external threads 107 for attachment of the implant 10.

Optionally, the tangent drive shaft 102 and the wound drive shaft 101 are both stainless steel tubes. The tangent drive shaft 102 and the winding drive shaft 101 are provided with bending adjusting sections at the distal ends and non-bending adjusting sections at the proximal ends. Transfer curved section to form a plurality of crisscross notches after cutting along the circumferencial direction, nevertheless every notch all does not cut off to guarantee that body rigidity has certain compliance again. The non-bending section is a straight stainless steel pipe. The bending sections of the tangent driving shaft 102 and the winding driving shaft 101 correspond to the bending sections of the sheath 113. In other words, when entering the bend adjustment section at the distal end of the sheath 113, the wound drive shaft 101 and the tangent drive shaft 102 located inside the sheath 113 are bent accordingly.

Referring to fig. 1 and 5, a steering handle 125 is attached to the proximal ends of the tangent drive shaft 102 and the wound drive shaft 101. Steering handle 125 is located outside the proximal end of bend adjustment handle 123.

The control handle 125 is provided with a winding drive switch 127, a tangent drive switch 128 and a travel switch 126. The wire drive switch 127 is coupled to the proximal end of the wire drive member 105 and is configured to control the rotation of the wire drive member 105. The tangent drive switch 128 is coupled to the proximal end of the tangent drive shaft 102 and is configured to control the rotation of the tangent drive shaft 102. The travel switch 126 is used to control the relative position between the tangent drive shaft 102 and the sheath 113.

Optionally, referring to fig. 5, the travel switch 126 and the winding driving switch 127 are disposed on one side (e.g., the upper side in fig. 5) of the control handle 125, and the tangent driving switch 128 is disposed on the other side (e.g., the lower side in fig. 5) of the control handle 125, and the arrangement may further enable the axial size of the control handle 125 to be relatively small, so that all switches can be held by one hand, thereby facilitating the operation.

Optionally, referring to fig. 9a to 9c, the claw 103 is a hollow structure. The jaws 103 are located at the distal end of the sheath 113 to secure the suture locking and severing device 100 to the guide 300, preferably by gluing. The claw 103 is sleeved on the periphery of the tangent driving shaft 102 near the distal end, i.e. the proximal end of the claw 103 is arranged between the inner wall of the distal end of the sheath 113 and the outer wall of the distal end of the tangent driving shaft 102. The distal ends of the tangent drive shaft 102 and the wound drive shaft 101 both extend beyond the distal end of the pawl 103. The radial dimension of the proximal end of the jaws 103 is smaller than the radial dimension of the distal end of the jaws 103, i.e. the jaws 103 are frustoconical, flared, etc. Referring to fig. 1, to facilitate delivery within the patient, the tube of the delivery assembly 20 is limited in size, and the radial dimension of the tube of the delivery assembly 20 is smaller than the outer diameter of the implant 10, so that the diameter of the jaws 103 gradually increases from the proximal end to the distal end until they conform to the outer diameter of the implant 10.

The distal end of the jaws 103 is removably connected to the implant 10. Specifically, as shown in fig. 9a, the distal end of the pawl 103 is provided with at least one fourth boss 115 (a third boss will be described later) for abutting against the implant 10. In this embodiment, the pawl 103 is symmetrically provided with two distally extending fourth bosses 115. Optionally, the claw 103 is made of a metal material, and the material of the claw 103 is preferably SUS 304.

The specific structure of the implant 10 provided herein is illustrated below with reference to the accompanying drawings.

Referring to fig. 10, the implant 10 includes a housing 4, a first position-limiting component 2, a rotating component 3, a thread-cutting component 5, a moving component 6, a winding component 7, a second position-limiting component 8, and a bottom shell 9.

Referring to fig. 10, the housing 4 is a cylinder with two open ends. In other words, the housing 4 is hollow and cylindrical. The housing 4 has an inner cavity 401.

Referring to fig. 8a, 8b, 11 and 12, the bottom case 9 covers the opening at the distal end of the housing 4 and is fixedly connected to the distal end of the housing 4. First spacing subassembly 2, runner assembly 3, removal subassembly 6, wire winding subassembly 7, the spacing subassembly 8 of second all are located shell 4 and set up along near-end to distal end's direction in proper order. The first stop assembly 2 is disposed at the proximal end of the housing 4 and is adjacent to the pawl 103. The rotating assembly 3 is connected to the distal end of the first limiting assembly 2 and fixes the first limiting assembly 2 in the housing 4. The tangent line assembly 5 is connected to the outer peripheral surface of the rotating assembly 3. The moving component 6 is matched with the rotating component 3 through teeth, and the winding component 7 is arranged at the far end of the moving component 6. The second limiting component 8 is connected with the far end of the winding component 7. The second limiting component 8 is fixedly connected with the bottom shell 9.

Referring to fig. 10, 13a and 13b, the proximal end of the housing 4 is provided with at least one second engaging groove 408 (the first engaging groove is described later) corresponding to the fourth protrusion 115 for detachably connecting with the distal end of the claw 103. Optionally, two second locking slots 408 are symmetrically disposed at the distal end of the housing 4 to ensure the connection stability.

Referring to fig. 11, when the distal end surface 116 of the claw 103 is engaged with the proximal end surface 406 of the housing 4, each fourth protrusion 115 is engaged with the corresponding second engaging groove 408 of the housing 4. In this way, the pawl 103 is rotated to drive the housing 4 to rotate axially. When the relative position of the tangent drive shaft 102 is fixed, the adjustment travel switch 126 may cause the claw 103 connected to the sheath 113 to maintain a relatively stationary state with the housing 4.

Referring to fig. 10, 13a and 13b, two symmetrical and axially extending second guide slots 404 (the first guide slot is described later) are provided at the distal end of the housing 4 for cooperating with two symmetrical third bosses 601 of the moving member 6. The second channel 404 connects the inner cavity 401 with the outside of the housing 4. The third protrusion 601 is engaged with the second guide groove 404, so that the moving component 6 and the housing 4 can only move relatively along the second guide groove 404, and the moving component 6 is prevented from rotating axially relative to the housing 4.

Referring to fig. 13a, 13c, 13d, 13e and 13f, the sidewall of the housing 4 is further protruded with a first guide slot 402 extending along the axial direction, and the first guide slot 402 penetrates through the distal end and the proximal end of the housing 4. The thread cutting assembly 5 is accommodated in the housing 4, in particular in the first guide groove 402.

Referring to fig. 13a, 13c, 13d, 13e and 13f, two symmetrical second through holes 410 and 411 (the first through hole will be described later) are further disposed on the side wall of the housing 4. One of the second through holes 411 is used for threading of the suture 200 into the implant 10. Another second through hole 410 extends radially through the first channel 402 for passage of the suture 200 out of the implant 10.

It will be appreciated that before the suture 200 is threaded into the implant 10, the two second through holes 410, 411 are in communication with the first through hole 712 of the winding assembly 7, so that the suture 200 can pass through the housing 4 in a radial direction through the second through hole 410, the inner cavity 401 and the second through hole 411 in sequence.

Referring to fig. 8a and 8b, the first position-limiting element 2 is fixed on the inner wall of the housing 4 near the proximal end surface of the housing 4. Preferably, the fixing connection is realized by adopting a laser electric welding mode.

Referring to fig. 14a to 14c, the first position-limiting assembly 2 includes a first base 205, a first stopping pawl 201 disposed on the first base 205, and a second elastic member 203. The first latch 201 is pivotally connected to the first base 205. The other end of the first latch claw 201 abuts against one end of the second elastic member 203. The second elastic member 203 is connected to the first base 205 through the first support 204.

Referring to fig. 14b, the first latch 201 has a first through hole 206 extending along the axial direction. The first base 205 is provided with a central axis hole 225, a second through hole 212 and a third through hole 211 which are arranged on the periphery of the central axis hole 225. The first base 205 has a central shaft hole 225 for passing the rotating assembly 3. The third through hole 211 is engaged with the first support 204, and the second through hole 212 is engaged with the first pin 202.

Referring to fig. 14a, the first latch 201 is pivotally connected to the first base 205 via a first pin 202. Specifically, one end of the first pin 202 is in clearance fit with the first through hole 206 of the first latch 201, and the other end of the first pin 202 is in clearance fit with the second through hole 212 of the first base 205.

Referring to fig. 14a, the other end of the first latch 201 is provided with a first inclined surface 210, and the first inclined surface 210 abuts against the rotating assembly 3 to limit the rotating direction of the rotating assembly 3.

Referring to fig. 14b and 14c, the second elastic element 203 is connected to the first base 205 through the first support 204, that is, the first support 204 is fixedly connected to the first base 205 and fixedly connected to the other end of the second elastic element 203. One end of the first support 204 is a cylinder 219 fixed in the third through hole 211, and the other end is fixedly connected to the second elastic member 203, and the specific shape is not limited as long as the second elastic member 203 can be accommodated.

Alternatively, the first base 205, the second elastic member 203, the first support 204, and the first pin 202 are made of weldable biocompatible metal, preferably SUS 304. Alternatively, the second elastic member 203 is a thin plate made of stainless steel.

Referring to fig. 15, the rotating assembly 3 includes a first ratchet 302, a rotating wheel 301 and a limiting ring 316.

Referring to fig. 16a to 16c, the rotating wheel 301 includes a first connecting rod 309 at the proximal end and a rotating rod 310 at the distal end. The first connection column 309 and the rotation column 310 are both hollow structures. The shaft hole of the first connecting column 309 is communicated with the shaft hole of the rotating column 310, and the size of the shaft holes is approximately the same. The first connecting post 309 has an outer diameter smaller than the outer diameter of the rotating post 310 to accommodate the first ratchet 302.

Referring to fig. 17a to 17c, the first ratchet 302 is sleeved on the outer peripheral surface of the first connecting post 309, and the distal end surface of the first ratchet 302 abuts against the proximal end surface 308 of the rotating post 310 and is fixedly connected by laser spot welding or the like. The outer rim of the first ratchet 302 has a plurality of rigid ratchet teeth or friction surfaces. In this embodiment, the outer rim of the first ratchet 302 has a plurality of ratchet teeth 306. The distal end 210 of the first stop pawl 201 of the first spacing assembly 2 is inserted into and engaged with the ratchet teeth 306 of the first ratchet 302. The first ratchet 302 is pushed by the ratchet 306 to move in steps and can only rotate in one direction, but not in reverse. When the first ratchet wheel 302 rotates counterclockwise, the first stopping pawl 201 is driven to swing, the second elastic member 203 abutting against the first stopping pawl 201 presses the first stopping pawl 201 to make the first stopping pawl always engaged with the ratchet 306 of the first ratchet wheel 302, at this time, the first stopping pawl 201 slides on the back of the teeth of the first ratchet wheel 302, and at the same time, the first stopping pawl 201 prevents the first ratchet wheel 302 from rotating clockwise.

Referring to fig. 17a to 17c, the first base 205 is sleeved on the outer peripheral surface of the first connecting column 309. The distal face of the first mount 205 is connected to the proximal face of the first ratchet 302. The inner wall of the central axial hole 225 of the first base 205 is fixedly connected to the outer circumferential surface of the first connecting post 309. The first latch 201, the second resilient member 203 and the first support 204 are disposed between a distal surface of the first base 205 and a proximal surface of the first connecting post 309. The interlayer formed by the proximal end surface of the rotating wheel 301 and the distal end surface of the first base 205 limits the first latch claw 201 from rotating around the first pin 202 and does not fall off.

Referring to fig. 17b, the limiting ring 316 is ring-shaped, is sleeved and fixed on the first connecting column 309 of the rotating wheel 301, and is pressed on the distal end of the first base 205. In other words, the retaining ring 316 and the first ratchet 302 sandwich the first base 205 to axially retain the first base 205.

Referring to fig. 17b, the distal end of the tangent driving shaft 102 is inserted into the shaft hole of the rotating component 3 and is in threaded connection with the shaft hole wall of the rotating component 3. Specifically, the shaft hole of the first connection column 309 of the rotating assembly 3 is provided with an internal thread 311 for cooperating with the external thread 107 of the tangent drive shaft 102, so that the first connection column 309 is threadedly connected with the distal end of the tangent drive shaft 102, thereby detachably connecting the implant 10 with the delivery assembly 20. Optionally, a portion of the internal thread 311 may also be disposed in the axial bore of the rotating post 310.

Referring to fig. 16c, the distal surface of the rotating post 310 is provided with four first helical teeth 314 along a circumferential array. The outer circumferential surface of the rotary post 310 is provided with a spiral passage 312 which gradually rises. Wherein the pitch of each first helical tooth 314 is smaller than the pitch of the helical channel 312, such that when the rotary wheel 301 is rotated, the first helical tooth 314 rises to a height smaller than the height at which the helical channel 312 rises. Alternatively, the first ratchet 302, the retainer ring 316 and the rotating wheel 301 are made of a biocompatible metal material, such as SUS 304.

Referring to fig. 10, the tangent line assembly 5 is disposed on the rotating assembly 3. Specifically, the tangent assembly 5 is disposed on the outer surface of the rotating column 310, and further, the tangent assembly 5 is disposed between the outer peripheral surface of the rotating assembly 3 and the inner wall of the inner cavity of the housing 4. Specifically, the thread cutting assembly 5 is disposed within the first guide slot 402. The proximal end of the tangent assembly 5 is disposed within the helical channel 312 to slidably engage the rotating assembly 3.

Referring to fig. 18a and 18b, the cutting line assembly 5 includes a blade holder 508 and a blade 505 secured to the distal end of the blade holder 508. The distal end of blade 505 is an obliquely disposed tip 504. The tip 504 of the blade 505 protrudes from the distal end face 503 of the blade holder 508 and faces the suture 200 exiting through the first through hole 712 to cut the suture 200. The distal end of the tool holder 508 is slotted to fix the blade 505 and the proximal end of the tool holder 508 is provided with a hemispherical boss 501 for engaging the helical channel 312 of the rotating wheel 301 to secure the tool holder 508 in the helical channel 312. The tool holder 508 is clearance fit with the first guide groove 402 of the housing 4. Thus, as the rotating wheel 301 rotates within the internal cavity 401 of the housing 4, the post 501 of the blade holder 508 and the helical channel 312 engage each other and the first guide channel 402 of the housing 4 cooperates with the blade holder 508 such that the blade 505 is gradually moved away from the distal end surface of the rotating wheel 301, gradually abutting the suture 200 and completing the process of cutting the thread. The blade holder 508 and the blade 505 are made of a biocompatible metal material, preferably SUS 304. The two can be integrated into one piece and also can be fastened and connected, and the connection mode is preferably laser welding.

Referring to fig. 8a and 8b, the proximal end of the moving element 6 abuts against the distal end of the rotating element 3.

Referring to fig. 19a to 19d, the moving assembly 6 is a hollow structure. The moving component 6 has a proximal shaft hole 607 and a distal shaft hole 605 at the center. The proximal axial hole 607 and the distal axial hole 605 communicate with each other. And, the diameter of the distal axial hole 605 is larger than that of the proximal axial hole 607, so that the shaft hole of the moving component 6 has a second step surface 606 facing to the distal end.

Alternatively, referring to fig. 8b, the diameter of the proximal shaft hole 607 of the moving member 6 is equal to the diameter of the shaft hole of the rotating wheel 301, so that the rotating link 104 is engaged with the winding member 7 through the proximal shaft hole 607 of the moving member 6.

Referring to fig. 19a to 19d, two third bosses 601 are symmetrically disposed on the outer surface of the distal end of the moving component 6, and respectively cooperate with the two second guide slots 404 at the distal end of the housing 4, so that the moving component 6 can only move axially in the second guide slots 404 and cannot rotate circumferentially. The proximal face of the moving assembly 6 is provided with four second helical teeth 608 which mesh with the first helical teeth 314 of the rotating wheel 301.

Referring to fig. 8a, when the tangent driving shaft 102 drives the rotating wheel 301 to rotate, the first helical tooth 314 of the rotating wheel 301 and the second helical tooth 608 of the moving assembly 6 generate a relative displacement. Since the rotating wheel 301 cannot move in the axial direction and the moving member 6 cannot rotate due to the restriction of the second guide groove 404 of the housing 4, the rotating wheel 301 rotates in place, and the moving member 6 does not rotate but gradually compresses the suture 200 away from the rotating wheel 301 in the distal direction. Meanwhile, during the rotation of the rotating wheel 301, the thread cutting assembly 5 moves axially distally under the restriction of the first guide groove 402, i.e., the blade of the thread cutting assembly 5 moves toward the suture 200. Since the ratio of the amounts of movement of the tangent element 5 and the moving element 6 in the same direction is equal to the ratio of the pitch of the spiral channel 312 to the pitch of the first helical tooth 314, and the pitch of the spiral channel 312 is greater than the pitch of the first helical tooth 314, the amount of displacement of the tangent element 5 is greater than the amount of displacement of the moving element 6. In other words, the tangent assembly 5 moves a greater distance distally than the moving assembly 6. The thread cutting assembly 5 is thus able to further cut the suture 200 as the moving assembly 6 moves to compress the suture 200.

Referring to fig. 8a, the distal end of the winding driving member 105 is detachably connected to the winding assembly 7 to drive the winding assembly 7 to rotate, so that the suture 200 is wound on the outer circumferential surface of the winding assembly 7.

Referring to fig. 20a to 20c, the winding assembly 7 includes a first elastic member 703, a winding shaft 702 and a second ratchet 701 sequentially disposed from a proximal end to a distal end.

Referring to fig. 20d to 20e, the bobbin 702 includes a second connecting post 714 at the distal end, a rotating portion 710 at the proximal end, and a wire passing portion 718 connected therebetween.

Referring to fig. 20d to 20e, the rotating portion 710 has a first engaging groove 703 extending along the axial direction. Referring to fig. 8a, the first protrusion 118 of the rotary connector 104 is disposed in the first slot 703, so that the first protrusion 118 rotates with the winding driving member 105 to drive the winding shaft 702 of the winding assembly 7 to rotate. Specifically, the first boss 118 may be a non-circular column such as a square block, a diamond block, or the like. The first locking groove 703 is shaped to fit the first protrusion 118.

Referring to fig. 20d to 20e, a first through hole 712 is formed in the thread passing portion 718 and is in a shape of a kidney and penetrates radially, and is used for threading the thread 200. In the initial state, both ends of the first through hole 712 communicate with the two second through holes 411, 410 of both sides of the housing 4, respectively.

Referring to fig. 8a, the first elastic member 703 may be a spring. The distal end of the first elastic member 703 abuts against the proximal end surface of the wire passing portion 718, and the other end abuts against the distal end surface of the moving assembly 6. Specifically, the distal end of the first elastic member 703 abuts against a step surface on the spool 712, and the proximal end of the first elastic member 703 abuts against the second step surface 606 of the moving assembly 6. Under the elastic force of the first elastic member 703, the moving component 6 and the rotating component 3 are attached together, i.e. the proximal inclined surface of the moving component 6 is closely attached to the distal inclined surface of the rotating component 3 under the action of the first elastic member 703. The distal end of the wire winding driving member 105 passes through the shaft hole of the moving assembly 6 and the first elastic member 703 abuts against the first locking groove 703 of the wire winding assembly 7.

Referring to fig. 20a to 20c, a plurality of ratchet teeth are disposed on the outer edge of the second ratchet 701. The second ratchet wheel 701 has a shaft hole 705, and the second connection post 714 of the winding shaft 702 extends into the inner surface of the second ratchet wheel 701 through the shaft hole 705 and then is fixedly connected. The proximal face 706 of the second ratchet 701 is tightly connected to the distal face 716 of the spool 702, including but not limited to laser spot welding. Optionally, the second ratchet 701 and the winding shaft 702 are made of a biocompatible metal material, preferably SUS 304.

As shown in fig. 21, the second position-limiting component 8 and the first position-limiting component 2 have substantially the same structure and material, and the second position-limiting component 8 is used for limiting the rotation direction of the second ratchet 701, so that the second ratchet 701 can only rotate counterclockwise.

Specifically, referring to fig. 8a, the second limiting member 8 is fixed to the inner wall of the housing 4 near the distal end surface of the housing 4.

Referring to fig. 21, the second position-limiting assembly 8 includes a second base 805, a second stopping claw 801 disposed on the second base 805, and a third elastic member 803. The second latch claw 801 is rotatably coupled to the second base 805. The other end of the second latch claw 801 abuts against one end of the third elastic member 803. The third elastic member 803 is connected to the second base 805 through the second support 804.

Referring to fig. 21, the second latch 801 has a fourth through hole 806 extending in the axial direction. The second base 805 is provided with a central shaft hole, and a fifth through hole (shielded by the second support 804) and a sixth through hole (shielded by the second support 804) which are arranged on the periphery of the central shaft hole. The central axial hole of the second base 805 is used for threading the distal end of the wire winding assembly 7. The sixth through hole is matched with the second support 804, and the fifth through hole is matched with the second pin shaft 802.

Referring to fig. 21, the second latch 801 is pivotally connected to the second base 805 by a second pin 802. Specifically, one end of the second pin shaft 802 is in clearance fit with the fourth through hole 806 of the second locking pawl 801, and the other end of the second pin shaft 802 is in clearance fit with the fifth through hole of the second base 805.

Referring to fig. 21, the other end of the second stopping pawl 801 is provided with a second inclined surface 810, and the second inclined surface 810 abuts against the ratchet teeth of the second ratchet 701 of the winding assembly 7 to limit the rotation direction of the winding assembly 7.

Referring to fig. 21, the third elastic element 803 is connected to the second base 805 through the second support 804, that is, the second support 804 is fixedly connected to the second base 805 and is fixedly connected to the other end of the third elastic element 803. One end of the second support 804 is a cylinder fixed in the sixth through hole, and the other end is fixedly connected to the third elastic member 803.

Alternatively, the second base 805, the third elastic member 803, the second support 804 and the second pin 802 are made of weldable biocompatible metal, preferably SUS 304. Alternatively, the third elastic member 803 is a thin plate made of stainless steel.

As shown in fig. 8a and 13a, the bottom shell 9 is fixedly connected to the inner wall of the housing 4 near the distal end surface 409 of the housing 4. The proximal face 902 of the bottom shell 9 coincides with the distal face 407 of the casing 4 and is fixedly connected, preferably laser welded.

As shown in fig. 22a to 22c, the bottom case 9 is provided with two through holes 903, 904 for connecting with the second base 805 of the second limiting component 8 through two pins. During assembly, the two pin shafts respectively pass through the two through holes 903 and 904 of the bottom case 9 and the two through holes 808 and 809 of the second base 805, so that one end of the two head ends of the pin shafts are overlapped and fixedly connected with the end surface 902 of the bottom case 9, the other end of the pin shafts are overlapped and fixedly connected with the proximal end surface of the second base 805 of the second limiting assembly 8, and the second stopping claw 801 and the second elastic member 803 are just located in an interlayer formed by the second base 805 of the second limiting assembly 8 and the bottom case 9. The bottom case 9 is made of a metal material, preferably SUS 304.

As shown in fig. 23a and 23b, in the initial state, both ends of the first through hole 712 of the wire passing portion 718 of the wire winding assembly 7 communicate with the two second through holes 411 and 410 on both sides of the housing 4, respectively. The free end of the suture 200 passes through the second through-hole 411, the first through-hole 712 of one side of the housing 4, and the second through-hole 410 of the other side of the housing 4 in this order.

Referring to fig. 8a, fig. 24a to fig. 24c, after the suture thread 200 penetrates through the implant 10 through the two second through holes 411, 410 and the first through hole 712, the winding driving shaft 101 is rotated clockwise to drive the rotating connecting member 104 to rotate in a plane, and further drive the winding shaft 702 (see fig. 20a) to rotate clockwise synchronously, so that the suture thread 200 is gradually wound on the outer circumferential surface of the thread passing portion 718 (see fig. 20e) of the winding shaft 702 to shorten the effective length of the suture thread 200.

Referring to fig. 8a, 25 and 26, when the suture 200 is contracted to an ideal state, the rotation of the winding driving shaft 101 is stopped, then the tangential driving shaft 102 is rotated clockwise, and since the thread 107 is a clockwise thread, the tangential driving shaft 102 drives the rotating wheel 301 (see fig. 17a) to rotate clockwise, so that the distal end surface 604 (see fig. 19b) of the moving assembly 6 gradually approaches the proximal end surface of the second base 805 (see fig. 21) of the second limiting assembly 8, thereby pressing the suture 200 between the distal end surface 604 of the moving assembly 6 and the proximal end surface of the second base 805 of the second limiting assembly 8, and at this time, another friction force is generated, and the double friction force can improve the locking force of the suture 200. In addition, while the suture 200 is locked, since the thread pitch of the spiral channel 312 (see fig. 16a) of the rotating wheel 301 is greater than the thread pitch of the first helical tooth 314 (see fig. 16a), the displacement amount of the thread cutting assembly 5 is greater than that of the moving assembly 6, so that the thread cutting assembly 5 cuts the free end of the suture 200. After the suture 200 is cut, the tangent driving shaft 102 is rotated counterclockwise, since the second ratchet 701 (see fig. 20a) connected to the rotating wheel 301 can only rotate clockwise but not counterclockwise under the action of the second limiting assembly 8, so that the tangent driving shaft 102 is disengaged from the rotating wheel 301, i.e. between the implant 10 and the delivery assembly 20, and then the delivery assembly 20 is withdrawn, thereby completing the locking and cutting of the suture 200.

The suture locking and cutting device 100 provided by the present invention is particularly suitable for interventional heart valve repair procedures, such as transcatheter mitral valve annuloplasty, transcatheter mitral valve rim-to-rim repair, and the like.

The utility model provides a process that suture locking cutting device 100 is used for mitral valve annuloplasty as follows: referring to fig. 27, at least two anchors 3000 are first implanted on the mitral valve annulus 2000, the anchors 3000 are connected to each other by a suture 200, and two free ends of the suture 200 extend out of the patient; the two free ends of the suture 200 are sequentially passed through the second through hole 411 at one side of the housing 4, the first through hole 712 of the bobbin 702 and the second through hole 410 at the other side of the housing 4 (see fig. 23 a); referring to fig. 28, the distal end of suture lock severing device 100 is delivered adjacent the mitral valve along suture 200; referring to fig. 2, the wound-wire driving shaft 101 is driven to rotate clockwise by the handle 125 outside the patient, and after the disappearance or the slightest state of mitral regurgitation is observed under ultrasound, the tangent-line driving shaft 102 is driven to rotate, so as to lock and cut the suture 200, and complete the mitral valve ring-contracting process, as shown in fig. 28.

The suture locking and cutting device 100 of the present invention can also be used for mitral valve edge-to-edge repair, the process is as follows: referring to fig. 29, a set of sutures 200 with spacers 4000 are implanted in the anterior leaflet and the posterior leaflet of the mitral valve, the sutures 200 and the spacers 4000 are U-shaped, and the free ends of the two sets of sutures 200 extend to the outside of the patient; referring to fig. 30, the free ends of the two groups of stitches 200 are sequentially inserted through the second through hole 411 and the first through hole 712 on one side of the housing 4 and the second through hole 410 on the other side of the housing 4 (see fig. 23 a); referring to fig. 31, the suture locking and cutting device 100 provided by the present invention is then sent to the area under the mitral valve, the winding driving shaft 101 is driven to rotate clockwise by the control handle 125 outside the patient, and after the disappearance of the mitral regurgitation or the minimal state is observed under ultrasound, the tangent driving shaft 102 is driven to rotate, so as to lock and cut the suture 200, thereby completing the edge-to-edge repair of the mitral valve, as shown in fig. 31.

The utility model provides a suture locking and cutting device 100 and a suture locking and cutting system 1000, which can wind and lock the suture 200 by driving the winding component 7 to rotate, and at the moment, the suture 200 can be locked by friction force for the first time; in the process that the driving thread cutting assembly 5 is gradually close to the thread 200, the thread 200 can be compressed for the second time through friction force, the locking force of the thread 200 can be improved through double friction force, and the thread 200 is cut off synchronously in the process of compressing the thread 200 for the second time, therefore, the thread locking and cutting device 100 provided by the utility model can realize the two processes of fixing and cutting the thread 200 through one device and one step without independently using the locking device and the thread cutting device, thereby greatly improving the function diversification and the structure compactness of the device; meanwhile, the suture locking and cutting device 100 provided by the utility model has little damage to the suture 200; the suture line 200 is locked by two different friction forces, the locking force is higher, and the processes of locking and cutting the suture line are more reliable; the cutting and the locking are realized simultaneously through one step, the operation time is shortened, and the operation risk is reduced.

The foregoing is a preferred embodiment of the present invention, and it should be noted that, for those skilled in the art, a plurality of improvements and decorations can be made without departing from the principle of the present invention, and these improvements and decorations are also considered as the protection scope of the present invention.

Claims (18)

1. A suture locking and cutting device, comprising:

the implant comprises a winding assembly and a tangent assembly, the winding assembly is provided with a first through hole for threading the suture, the tangent assembly comprises a blade, and the blade faces the suture passing through the first through hole; and

the conveying assembly comprises a tangent driving shaft and a winding driving piece movably arranged in the tangent driving shaft in a penetrating mode, and the far end of the winding driving piece is detachably connected with the winding assembly to drive the winding assembly to rotate so that the suture can be wound on the outer peripheral face of the winding assembly; the distal end of the tangent drive shaft is removably attached to the tangent assembly to move the blade toward the suture and sever the suture.

2. The suture locking and cutting device of claim 1, wherein the proximal end of the winding assembly has a first slot, the distal end of the winding driving member has a first protrusion adapted to fit into the first slot, the first protrusion is disposed in the first slot, and the first protrusion rotates the winding assembly when the first protrusion rotates with the winding driving member.

3. The suture locking and cutting device of claim 2, wherein the wire drive member includes a wire drive shaft and a rotational coupling member, the rotational coupling member including a second boss, an intermediate boss, and the first boss integrally interconnected, the second boss being disposed at a distal end of the wire drive shaft, the second boss and the intermediate boss forming a first step surface therebetween, the wire drive shaft abutting the first step surface.

4. The suture locking and cutting device of any one of claims 1 to 3, wherein the implant further comprises a housing and a bottom shell covering a distal end of the housing, the winding assembly and the thread cutting assembly are both disposed within the housing, and the winding assembly is proximate to the bottom shell.

5. The suture locking and cutting device of claim 4, wherein the implant further comprises a rotating assembly disposed within the housing on a side of the winding assembly facing away from the base housing, the tangent drive shaft being threaded and threadedly coupled within a shaft bore of the rotating assembly; the outer peripheral surface of the rotating assembly is provided with a spiral channel, the tangent assembly is arranged between the outer peripheral surface of the rotating assembly and the inner wall of the shell, and the near end of the tangent assembly is in sliding connection with the rotating assembly in the spiral channel.

6. The suture locking and cutting device of claim 5, wherein the side wall of the housing is provided with a first guide groove in an axial direction, and the tangent line assembly is accommodated in the housing and the first guide groove.

7. The suture locking and cutting device of claim 6, wherein the side wall of the housing is further provided with two second through holes symmetrically arranged, wherein one of the second through holes is used for the suture to penetrate into the implant, and the other second through hole is communicated with the first guide groove and is used for the suture to penetrate out of the implant.

8. The suture locking and cutting device of claim 7, wherein two of the second through holes are in communication with the first through hole of the winding assembly prior to the suture being threaded into the implant.

9. The suture locking and cutting device of claim 5, wherein the implant further comprises a moving assembly disposed within the housing, a proximal end of the moving assembly abuts a distal end of the rotating assembly, a shaft hole of the moving assembly has a second stepped surface facing the distal end, a proximal end of the winding assembly includes a first elastic member elastically abutting the second stepped surface, and a distal end of the winding driving member passes through the shaft hole of the moving assembly and the first elastic member to abut a first engaging groove of the winding assembly.

10. The suture locking and cutting device of claim 9 wherein the housing further defines at least one second channel, and wherein the outer peripheral surface of the moving assembly defines at least one third projection that engages the second channel to prevent axial rotation of the moving assembly relative to the housing.

11. The suture locking and cutting device of claim 9 wherein the distal end of the rotating assembly is circumferentially provided with a first plurality of beveled teeth and the proximal end of the moving assembly is circumferentially provided with a second plurality of beveled teeth that engage the first plurality of beveled teeth.

12. The suture locking and cutting device of claim 11, wherein a pitch of the helical channel is greater than a pitch of the first helical tooth.

13. The suture locking and cutting device of claim 5, wherein the proximal end of the rotating assembly is provided with a first ratchet wheel, the implant further comprises a first base and a first stop pawl and a second elastic member arranged on the first base, the first base is connected with the proximal end of the first ratchet wheel, the first stop pawl is rotatably connected with the first base, one end of the first stop pawl is meshed with the ratchet teeth of the first ratchet wheel, and the other end of the first stop pawl abuts against one end of the second elastic member.

14. The suture locking and cutting device of claim 5, wherein the distal end of the winding assembly is provided with a second ratchet wheel at the proximal end of the rotating assembly, the implant further comprises a second base, a second stopping pawl and a third elastic member, the second stopping pawl and the third elastic member are arranged on the second base, the second base is connected with the distal end of the second ratchet wheel, the second stopping pawl is rotatably connected with the second base, one end of the second stopping pawl is meshed with the ratchet teeth of the second ratchet wheel, and the other end of the second stopping pawl abuts against one end of the third elastic member.

15. The suture locking and cutting device of claim 4, wherein the delivery assembly further comprises a pawl located at a distal end of the tangent drive shaft, and wherein the distal end of the pawl is removably coupled to a proximal end of the housing of the implant.

16. The suture locking and cutting device of claim 15, wherein the distal end of the jaw is provided with at least one fourth boss, the proximal end of the housing is provided with at least one second slot corresponding to the fourth boss, and the fourth boss is inserted into the second slot of the housing.

17. The suture locking and cutting device of claim 15, further comprising a control handle coupled to the proximal end of the delivery assembly, the control handle having a wire drive switch and a wire cut drive switch, the wire drive switch coupled to the proximal end of the wire drive member and configured to control rotation of the wire drive member; the tangent line drive switch is connected to the near end of the tangent line drive shaft and is used for controlling the tangent line drive shaft to rotate.

18. A suture locking and cutting system, comprising a guiding device and the suture locking and cutting device as claimed in any one of claims 1 to 17, wherein the guiding device comprises a sheath and a bending handle connected with the proximal end of the sheath, the winding driving member and the tangent driving shaft are arranged in the guiding device in a penetrating way, and the distal end of the conveying assembly is positioned outside the distal end of the sheath and abuts against the sheath.

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