Stent delivery system

Abstract

The invention provides a stent conveying system. The stent conveying system comprises a tube body, a stent loading area arranged at the far end of the tube body and a connecting piece. The stent loading area is used for loading a stent, and the pipe section, close to the stent loading area, of the pipe body is sleeved with an anchoring piece. The anchoring piece is configured to have a locking state and an unlocking state, and when the anchoring piece is in the locking state, the connecting piece is connected with the anchoring piece and the support at the same time; when the anchoring piece is in the unlocking state, the connecting piece is disconnected from the anchoring piece or the support; the anchoring piece is arranged at the near end of the stent, and the anchoring piece is in the locking state before the stent reaches the release position, so that the stent is pulled, the stent is prevented from slipping and falling into a blood vessel in the in-vivo conveying process, unnecessary medical accidents are avoided, and the safety in the stent conveying process is ensured.

Description

Technical Field

[0001] The present invention relates to the technical field of medical devices, and particularly to a stent delivery system. Background Art

[0002] The advantage of an expandable vascular stent relative to a self-expanding stent is that it can be accurately positioned during release, has a small delivery outer diameter, and can well conform to the shape of the blood vessel after the stent is expanded, reducing the stress stimulation on the blood vessel. Therefore, it is currently widely used in the treatment of vascular stenosis lesions, mostly for the treatment of iliac artery stenosis lesions. Of course, there are also some extended applications, such as for the reconstruction of aortic branch vessels.

[0003] Currently, for balloon-expandable stents on the market, the stent is usually directly pressed onto the surface of the folded balloon through a dedicated device. There is no other force between the stent and the balloon except for friction to keep the two firmly connected or restrict movement. This makes it easy for the stent to move relative to the folded balloon or even slip off the balloon when the balloon pushes the stent into the human body cavity. Once the stent slips off the balloon and into the human body during the process of delivering the stent into the body, it will cause catastrophic consequences to the patient. Summary of the Invention

[0004] Based on this, it is necessary to provide a new stent delivery system that can avoid slipping from the delivery device into the human blood vessel during the stent delivery process, resulting in unnecessary medical accidents.

[0005] A stent delivery system includes a tube body, a connecting member, and a stent loading area provided at the distal end of the tube body. The stent loading area is used for loading a stent, and an anchor is sleeved on the tube section of the tube body near the stent loading area. The anchor is configured to have a locked state and an unlocked state. When the anchor is in the locked state, the connecting member connects the anchor and the stent. When the anchor is in the unlocked state, the connecting member releases the connection with the anchor or the stent.

[0006] In one embodiment, the anchor includes a lock core, and a lock groove is provided on the circumferential side wall of the anchor. The anchor is axially provided with a core through hole that penetrates the axial side walls of the lock groove. The lock core is inserted into the core through hole and can slide axially along the core through hole. When the lock core simultaneously passes through the axial side walls of the lock groove, the anchor is in the locked state.

[0007] In one embodiment, the connecting member is flexible and includes a loop-shaped connecting member loop portion connected end to end. When the anchor is in the locked state, at least a part of the loop-shaped connecting member loop portion is sleeved on the lock core in the lock groove.

[0008] In one embodiment, the connecting member includes a fixed end and a free end. The fixed end is fixedly connected to the distal end of the anchoring member; the free end includes the loop portion of the loop-shaped connecting member. When the anchoring member is in the locked state, the free end hooks the bracket and then sleeves on the lock core in the lock groove.

[0009] In one embodiment, the loop portion of the loop-shaped connecting member includes a fixed portion and a free portion. The fixed portion is fixedly sleeved on the proximal end of the bracket. When the anchoring member is in the locked state, the free portion is sleeved on the lock core in the lock groove.

[0010] In one embodiment, the perimeter of the loop portion of the loop-shaped connecting member is greater than or equal to the perimeter of the bracket after expansion.

[0011] In one embodiment, the extendable length of the free portion of the loop portion of the loop-shaped connecting member is greater than the distance from the proximal end of the bracket to the lock groove.

[0012] In one embodiment, a first lumen is provided in the tube body. The distal port of the first lumen communicates with the outside on the distal side of the tube body close to the anchoring member. The lock core can slide axially in the first lumen, pass out from the distal port, and then penetrate into the through-core hole from the proximal end of the anchoring member.

[0013] In one embodiment, the stent loading area includes a balloon body. The stent can be mounted on the balloon body; a fixing member is provided on the proximal surface of the balloon body. One end of the lock core is connected to the fixing member, and the other end can extend to the distal end of the anchoring member and penetrate into the through-core hole.

[0014] In one embodiment, the fixing member is elastic. The balloon body includes a first state of radial contraction and a second state of radial expansion. When the balloon body is in the first state, the lock core can pass through the axial side walls of both sides of the lock groove at the same time; when the balloon body is in the second state, the lock core at least disengages from the proximal side wall of the lock groove.

[0015] The beneficial effects of the present invention are as follows: Compared with the prior art, the present invention provides a stent delivery system, including a tube body, a stent loading area provided at the distal end of the tube body, and a connecting member; the stent loading area is used for loading a stent, and an anchoring member is sleeved on the tube section of the tube body close to the stent loading area; the anchoring member is configured to have a locked state and an unlocked state. When the anchoring member is in the locked state, the connecting member connects the anchoring member and the stent at the same time; when the anchoring member is in the unlocked state, the connecting member releases the connection with the anchoring member or the stent; by providing an anchoring member at the proximal end of the stent, the anchoring member is in the locked state before the stent reaches the release position, thereby pulling the stent to prevent the stent from slipping off and falling into the blood vessel during the in-vivo delivery process, causing unnecessary medical accidents, and ensuring the safety during the stent delivery process. Brief Description of the Drawings

[0016] Figure 1 This is a schematic diagram of the overall structure of the stent delivery system of the present invention.

[0017] Figure 2 This is a schematic diagram of the structure of the anchoring member in the first embodiment of the present invention.

[0018] Figure 3 This is a schematic diagram of the structure of the fixing holes on the anchoring member in the first embodiment of the present invention.

[0019] Figure 4 This is a schematic diagram of the structure of the first pipe section and the disconnection groove in the first embodiment of the present invention.

[0020] Figure 5 This is a schematic diagram of the structure where the lock core penetrates through the first pipe section in the first embodiment of the present invention.

[0021] Figure 6 This is a cross-sectional schematic diagram of the first pipe section of the pipe body in the first embodiment of the present invention.

[0022] Figure 7 This is a cross-sectional schematic diagram of the first pipe section of the pipe body in another embodiment in the first embodiment of the present invention.

[0023] Figure 8 This is a schematic diagram of the structure where the anchoring member is fixedly connected to the connecting member in the first embodiment of the present invention.

[0024] Figure 9 This is a schematic diagram of the unlocked state of the anchoring member in the second embodiment of the present invention.

[0025] Figure 10 This is a schematic diagram of the structure of the connecting member after the stent is expanded in the second embodiment of the present invention.

[0026] Figure 11 This is a schematic diagram of the structure of the connecting member before the stent is expanded in the second embodiment of the present invention.

[0027] Figure 12 This is a schematic diagram of the structure of the anchoring member in the third embodiment of the present invention.

[0028] Figure 13 This is a schematic diagram of the structure of the wire groove on the anchoring member in the third embodiment of the present invention.

[0029] Figure 14 This is a schematic diagram of the structure of the base in the fourth example of the present invention.

[0030] Figure 15 This is a schematic diagram of Step 1 in the fifth embodiment of the present invention.

[0031] Figure 16 This is a schematic diagram of Step 2 in the fifth embodiment of the present invention.

[0032] Figure 17 It is a schematic diagram of balloon pressurization in the second step of the fifth embodiment of the present invention.

[0033] Figure 18 It is a schematic diagram of the third step in the fifth embodiment of the present invention.

[0034] Figure 19 It is a schematic diagram of the structure of the stent delivery system in the sixth embodiment of the present invention.

[0035] Figure 20 It is a schematic diagram of the connection structure between the fixing member provided on the balloon body and the lock core in the sixth embodiment of the present invention.

[0036] Figure 21 It is a schematic diagram of the structure of the balloon body in the second state in the sixth embodiment of the present invention.

[0037] Figure 22 It is a schematic diagram of the structure of the balloon body in the first state in the sixth embodiment of the present invention.

[0038] Figure 23 It is a schematic diagram of the structure when the balloon body expands to the maximum balloon diameter state in the sixth embodiment of the present invention.

[0039] Figure 24 It is a schematic diagram of the structure when a wire passing hole is provided on the anchoring member in the seventh embodiment of the present invention.

[0040] Figure 25 It is a schematic diagram of the structure when the connecting member is hooked on the lock core when the balloon body is not expanded in the seventh embodiment of the present invention.

[0041] Figure 26 It is a schematic diagram of the state structure when the connecting member disengages from the lock core when the balloon body expands in the seventh embodiment of the present invention. Detailed implementation manners

[0042] To better understand the concept of the present invention, the following specifically describes the implementation manners of the present invention with reference to the accompanying drawings. The following specific embodiments are only partial embodiments of the present invention and do not limit the present invention.

[0043] For ease of description, spatial relative relationship terms may be used in the text to describe the relationship of one element or feature shown in the figure relative to another element or feature. These relative relationship terms are, for example, "inner", "outer", "inner side", "outer side", "below", "beneath", "above", "over", etc. Such spatial relative relationship terms are intended to include different orientations of the device in use or operation other than the orientations depicted in the figure. For example, if the device in the figure is flipped, then an element described as "below" or "beneath" another element or feature will subsequently be oriented as "above" or "over" the other element or feature. Thus, the exemplary term "below" can include both upward and downward orientations. The device may be otherwise oriented (rotated 90 degrees or in other directions) and the spatial relative relationship descriptors used in the text are interpreted accordingly.

[0044] Although terms such as first, second, third, etc. may be used in the text to describe multiple elements, components, regions, layers, and / or sections, these elements, components, regions, layers, and / or sections should not be limited by these terms. These terms may be used only to distinguish one element, component, region, layer, or section from another region, layer, or section. Unless the context clearly indicates otherwise, terms such as "first", "second", and other numerical terms do not imply an order or sequence when used in the text. Thus, the first element, component, region, layer, or section discussed below may be referred to as the second element, component, region, layer, or section without departing from the teachings of the exemplary embodiments.

[0045] To more clearly describe the structure of the present application, the terms "proximal" and "distal" are defined herein as commonly used terms in the field of interventional medicine. Specifically, "distal" refers to the end away from the operator, and "proximal" refers to the end close to the operator. For example, during stent implantation, the end inserted into the human body is the distal end, and the end held or operated by the operator is the proximal end; "axial" refers to its length direction, and "radial" refers to the direction perpendicular to the "axial" direction.

[0046] Example 1:

[0047] Please refer to Figure 1 and Figure 2, the stent delivery system 100 provided by the present application generally includes a stent delivery device and a stent 5. The stent delivery device generally includes a tube body 1, a stent loading area 4 provided at the distal end of the tube body 1, and a base 6 provided at the proximal end of the tube body 1. The stent loading area 4 is generally used to load the stent 5, and an anchor 2 is sleeved on the tube section of the tube body 1 close to the stent loading area 4. Among them, the anchor 2 is preferably a cylindrical structure. The anchor 2 is axially provided with a connection hole 22, and the aperture of the connection hole 22 is equal to the aperture of the tube body 1. The anchor 2 is sleeved on the tube body 1 through the connection hole 22 and fixed on the tube body 1 by bonding or welding. The anchor 2 can be processed from a metal material or a polymer material, and is preferably made of stainless steel material (304 or 316L) or polyetheretherketone (peek) material, etc. The anchor 2 is configured to have a locked state and an unlocked state. When the anchor 2 is in the locked state, the connecting member connects the anchor 2 and the stent 5 at the same time, by means of hooking or fixed connection. When the anchor 2 is in the unlocked state, the connecting member releases the connection with the anchor 2 or the stent 5. It can be understood that when the anchor 2 is in the unlocked state, the connecting member releases the connection relationship with at least one of the anchor 2 or the stent 5, so that the stent 5 is in a free state of detaching from the anchor 2. This situation is usually unlocked when the stent 5 is safely delivered to the position to be released, so that the stent 5 can stay in the blood vessel and the delivery device can be safely withdrawn from the blood vessel. When the anchor 2 is in the locked state, it is usually during the process of delivering the stent 5 to the target area in the blood vessel. During this process, the stent 5 is usually in an undilated and folded state. At this time, it is necessary to ensure that the stent 5 is firmly installed in the stent loading area 4 to avoid slipping. By connecting the stent 5 and the anchor 2 through the connecting member, its slipping can be effectively avoided and it can safely reach the designated delivery position.

[0048] Among them, the stent 5 can be a covered stent, that is, it includes an expandable metal skeleton (corrugated ring) and a film covering the surface of the metal skeleton; it can also be a bare stent without a film. When the connecting member is connected, it is movably connected or fixedly connected to the skeleton or corrugated ring at the proximal end of the stent 5. Among them, when the connecting member is connected to the skeleton or corrugated ring at the proximal end of the stent 5, it can be connected to part of the corrugated rings or all of the corrugated rings, which can be set according to specific needs.

[0049] In this embodiment, please continue to refer to Figures 1 - 3, the anchoring member 2 includes a lock core 7, and a lock groove 21 is formed on the side wall of the anchoring member 2. The anchoring member 2 is axially provided with a core passing hole 23 which penetrates through the axial side walls of the lock groove 21. The lock core 7 is inserted into the core passing hole 23 and can slide axially along the core passing hole 23. The lock core 7 and the lock groove 21 cooperate to form a locking structure similar to a bolt structure. The core passing hole 23 penetrates through the axial side walls of the lock groove 21, so that when the lock core 7 passes through between the core passing holes 23, an axial blocking structure is formed for the lock groove 21, thereby restricting the connecting member sleeved in the lock groove 21 within the lock groove 21 to form a restricting structure for the connecting member; when the lock core 7 slides in the core passing hole 23 and passes through both side walls at the same time, the lock core 7 axially blocks the lock groove 21, and at this time the anchoring member 2 is in a locked state; when the lock core 7 only penetrates one side wall, that is, the lock core 7 only penetrates into the core passing hole 23 on the side of the side wall of the anchoring member 2 close to the proximal end of the lock groove 21, at this time the lock core 7 does not completely enclose the lock groove 21, or does not enclose the lock groove 21 at all, then the anchoring member 2 is in an unlocked state.

[0050] In a preferred embodiment, please continue to refer to Figure 2 and Figure 3 , the lock groove 21 is formed between the proximal end face and the distal end face of the anchoring member 2, wherein the lock groove 21 is arranged closer to the proximal end face side, so that the anchoring member 2 forms a first core passing part 25 at the proximal end of the lock groove 21 and a second core passing part 26 at the distal side of the lock groove 21, and the axial length of the second core passing part 26 is greater than the axial length of the first core passing part 25. With such a setting, the lock core 7 penetrates into the proximal side of the first core passing part 25 and penetrates out from the distal side, crosses the lock groove 21 and then penetrates into the proximal side of the second core passing part 26 and is hidden in the second core passing part 26 to form a locking structure; with such a setting, since the axial length of the second core passing part 26 is greater than the axial length of the first core passing part 25, when the lock core 7 is subjected to a non-axial pulling force, it can effectively prevent the lock core 7 from coming out of the second core passing part 26 and avoid the destruction of the locking structure; preferably, the axial length of the second core passing part 26 is greater than the axial length of the lock groove 21; wherein, there is a distance between the core passing hole 23 and the bottom of the lock groove 21, so that when the lock core 7 is locked, a gap is formed with the bottom of the lock groove 21, which is convenient for the connecting member to be sleeved in the lock groove 21; in one embodiment, the anchoring member 2 is a cylindrical structure with an outer diameter of 2-3 mm and a total length of 9-12 mm, and there is a core passing hole 23 and a mounting hole for sleeving on the pipe body 1 in the middle. The distal end head of the pipe body 1 passes through the mounting hole, and the lock core 7 passes through the core passing hole 23. There is a groove structure in the middle of the anchoring member 2, and the length of the groove structure is 3-4 mm. A rope loop, that is, a loop connecting part, passes through here; the diameter of the mounting hole is 1.5-2 mm, and the aperture of the core passing hole 23 is 0.4-0.6 mm.

[0051] In a preferred embodiment, not shown in the figure, the lock core 7 is an elastic metal wire, and the head at the front end has a bent structure. A bent hole section adapted to the bent structure of the head at the front end of the lock core 7 is provided at the distal end of the core passing hole 23 in the second core passing part 26. With such a setting, after the front end of the lock core 7 is inserted into the second core passing part 26 and reaches the bent hole section, the bent structure and the bent hole section can form an inverted hanging structure, thereby further preventing the lock core 7 from being pulled out of the second core passing part 26 when subjected to a non-axial pulling force, and avoiding damage to the locking structure. Since the lock core 7 is an elastic metal wire, when the lock core 7 is retracted to release the lock, only a greater retracting force is required to be pulled out from the core passing hole 23 of the second core passing part 26 to achieve unlocking.

[0052] In this embodiment, please refer to Figure 4 and Figure 5 and, a base 6 is provided at the proximal end of the tube body 1. The base 6 includes a core wire pipeline 61. A first lumen 11 is provided in the tube body 1. One end of the first lumen 11 extends to a position close to the anchor 2, and the other end communicates with the core wire pipeline 61. The base 6 is usually located outside the human body during the use of the delivery device to establish a passage from outside the body to inside the body. The lock core 7 enters from the proximal end inlet of the core wire pipeline 61, enters the first lumen 11 via the core wire pipeline 61, and thus extends along the first lumen 11 to the position of the anchor 2 and is connected to the anchor 2. The lock core 7 extends in the first lumen 11 and the core wire pipeline 61 and can slide axially. During use, the operator controls the lock core 7 exposed from the core wire pipeline 61 at the position of the base 6, thereby controlling the axial sliding of the lock core 7 in the first lumen 11 and the core wire pipeline 61. Preferably, an operation handle 81 for facilitating the operator to hold is connected to the part of the lock core 7 exposed from the core wire pipeline 61. The operation handle 81 and the lock core 7 are fixedly connected by integral injection molding connection or bonding or by mechanical locking. Among them, the base 6 further includes a guide wire pipeline 63. The tube body 1 includes a third lumen 12. One end of the third lumen 12 communicates with the guide wire pipeline 63, and the other end penetrates through the distal end of the tube body 1. The guide wire pipeline 63 is used to introduce the guiding guide wire of the delivery device to guide the delivery device to reach the specified blood vessel passage. The third lumen 12 and the first lumen 11 are usually separately isolated and not communicated with each other.

[0053] In this embodiment, please refer to Figure 5 and Figure 9, the tube body 1 does not extend the entire tube body 1 for the tube section containing the first lumen 11, but only extends from the proximal end of the tube body 1 to a position near the proximal end of the anchor 2, and has a certain spacing distance from the anchor 2; and both ends of the first lumen 11 are through. When the lock core 7 extends to the distal end of the first lumen 11 near the anchor 2, it penetrates outside the tube body 1. Preferably, a disconnection groove 103 is provided in the tube section of the tube body 1 connected to the proximal end of the anchor 2, and the part of the tube body 1 where the disconnection groove 103 is located and contains the first lumen 11 is truncated, so that the distal end of the first lumen 11 is through, the first lumen 11 communicates with the side wall of the disconnection groove 103, and the lock core 7 penetrates through the side wall and then into the core through hole 23.

[0054] In another embodiment, please refer to Figure 6 and Figure 7 , the tube body 1 includes a first tube section 101 provided with a first lumen 11 and a second tube section 102 not provided with a first lumen 11. The first tube section 101 is arranged near the proximal end, and the second tube section 102 is arranged near the distal end. The anchor 2 is arranged on the second tube section 102 and near the position of the first tube section 101, and has a certain distance from the first tube section 101. Among them, the first tube section 101 can be coaxial with the second tube section 102 and have an outer diameter larger than that of the second tube section 102, so that the tube body 1 forms a stepped structure at the junction of the first tube section 101 and the second tube section 102. The first lumen 11 is arranged in the part of the first tube section 101 that radially exceeds the second tube section 102, so as to form a structure with both ends of the first lumen 11 being through, so that the lock core 7 can penetrate out of the distal end of the first lumen 11 and then penetrate into the core through hole 23 of the anchor 2.

[0055] In this embodiment, the connecting piece is flexible and can be a polymer wire with good biocompatibility, such as polypropylene (PP), high-density polyethylene (HDPE), polytetrafluoroethylene PTFE or PET, etc. Since PTFE has good biocompatibility and mechanical strength, PTFE wire is preferably used in this embodiment. The connecting piece 3 includes a folded loop-shaped connecting part 3a, and the loop-shaped connecting part 3a is used to sleeved on the lock core in the lock groove to achieve locking. The connecting piece 3 can be an integrally formed polymer coil, or can be formed by tying a knot at both ends of the polymer wire to form a ring shape, or can be formed by folding a section of polymer material to form two sections, and the folded part of the two sections forms the loop-shaped connecting part 3a. The free ends of the two sections far from the loop-shaped connecting part 3a can be connected to the bracket or to the anchor. When the anchor 2 is in the locked state, the loop-shaped connecting part 3a of the connecting piece 3 is sleeved in the lock groove 21 to realize the connection of the anchor 2, and the connecting piece 3 is connected to the bracket 5, so as to anchor the bracket 5 and the anchor 2 together to avoid slipping;

[0056] In this embodiment, please refer to Figure 8, the fixed connection end of the connecting member 3 is located on the anchoring member 2. When the anchoring member 2 is in the unlocked state, the connecting member 3 releases the connection with the bracket 5; preferably, the connecting member 3 includes a fixed end 31 and a free end 32. The fixed end 31 is fixedly connected to the anchoring member 2. The connecting member 3 and the anchoring member 2 can be fixedly connected in various ways, such as welding, bonding or crimping, etc. A fixing hole 27 can be opened on the distal end face of the anchoring member 2, and the fixed end 31 of the connecting member 3 is connected to the fixing hole 27. The fixing hole 27 can also be opened on the side wall or other positions of the anchoring member 2; when the anchoring member 2 is in the locked state, the free end 32 of the connecting member 3 extends to the proximal position of the bracket 5, and after passing through or winding around the wave loops or the skeleton at the proximal end of the bracket 5, it hooks the bracket 5 and then sets the free end 32 in the locking groove 21. At this time, the lock core 7 passes through the core holes 23 on both side walls of the locking groove 21 at the same time to complete the hooking connection between the anchoring member 2 and the bracket 5. In other embodiments, the connecting member 3 is at least provided on the free end 32 of the connecting member, and the fixed end 31 may not be provided with a ring shape and is connected to the free end 32 by means of a silk thread.

[0057] Embodiment 2:

[0058] In this embodiment, please refer to Figure 9 - FIG. 1. The structure of the conveyor is substantially the same as that in Embodiment 1. The difference is that the fixed connection end of the connecting member 3 is located on the bracket 5. When the anchoring member 2 is in the unlocked state, the connecting member 3 releases the connection with the anchoring member 2; preferably, the connecting member 3 includes a fixed part 33 and a free part 34. At least the fixed part 33 is fixedly sleeved on the proximal end of the bracket 5. During the production of the bracket 5, the connecting member 3 is threaded through the wave loops at the proximal end of the bracket 5, so as to be sleeved on the bracket 5; in order to further ensure the firmness of the annular connection, the connecting member 3 can be knotted on the metal wave rod at one of the wave angles to ensure that even if the connecting member 3 breaks, it will not separate from the bracket 5, ensuring safety; further, the connecting member 3 forms a closed rope loop by tying dead knots at both ends. In this way, when the bracket 5 is in a compressed state without expansion and release, a part of the connecting member 3 is fixedly sleeved on the proximal end of the bracket 5 to form the fixed part 33, and the other part forms the free part 34. When the anchoring member 2 is in the locked state, the free part 34 (i.e., the free end) of the connecting member 3 is sleeved in the locking groove 21 to form a connection structure with the anchoring member 2, preventing the bracket 5 from slipping off and falling into the blood vessel lumen.

[0059] In this embodiment, the circumference of the connector 3 is greater than the circumference of the stent 5 after expansion. The purpose of such a setting is that, first, the connector 3 can be tightened as the stent 5 expands, and is wrapped around the circumferential extension of the proximal wave coil of the stent 5. Therefore, the circumference of the connector 3 needs to be greater than the circumference of the stent 5 after expansion to avoid the connector 3 limiting the expansion of the stent 5, and also to avoid the expansion of the stent 5 from breaking the connector 3; preferably, the circumference of the connector 3 only needs to be slightly greater than the circumference of the stent 5 after expansion, and does not need to be too long. This is to avoid the length of the connector 3 that is not supported by the stent 5 being too long, resulting in the connector 3 floating in the blood vessel after the stent 5 is implanted, causing unpredictable problems; in an implemented example, the stent 5 is expected to have a diameter of 2.7mm in the unexpanded state and a diameter of 10mm in the expanded state, then the circumference length L of the connector 3 needs to be slightly greater than the circumference of the stent 5 after expansion, that is, it needs to be greater than 10*π, then the circumference length L of the connector 3 = 10*π + 3~4mm.

[0060] Reference Figures 24 - 26 In other embodiments, in order to reduce the circumferential constraint of the stent by the connector 3, and to avoid the connector 3 from being too much floating after the stent is deployed, which may affect the blood flow. Alternatively, the length of the connector 3 around the proximal end of the stent is greater than or equal to the arc length of the corresponding part after the stent is expanded. In this embodiment, the connector 3 is folded back to form two strands by an integral line segment, such as Figure 26 The first strand 3b and the second strand 3c in the integral line segment have two free ends after being folded back, and both free ends are connected to the proximal end of the bracket and relatively fixed. The fixing method can be connected to the proximal end coating 52 of the bracket 5, or connected to the wave coil 51 at the proximal end of the bracket 5, for example, it can be wound around the wave rod of one of the wave coils 51 and fixed relatively to the wave coil 51, for example, it can be connected to the wave rod and then tied to form a fixed knot 3d, and the other segments can be wrapped around the circumference of the bracket 5 and then extended axially, so that the circular connection part 3a between the first strand 3b and the second strand 3c can be hooked on the lock core 7. In this embodiment, in order to allow the connector 3 to be stably wound around the outer wall of the stent along the outer wall of the stent after the stent is deployed, a plurality of fixing rings 53 are provided on the outer wall of the stent 5 along its circumferential direction. The connector 3 passes through the fixing rings 53 and can move circumferentially relative to the fixing rings 53. After the stent 5 is deployed, the connector 3 is continuously pulled and gradually wound around the outer wall of the stent 5 as the stent 5 is deployed. In this manner, the length of the connector 3 and the fixed positions of the two ends of the free end of the connector 3 and the stent can be determined according to the length required for axial hooking on the lock core 7 and the circumference of the deployed stent, so as to meet the hooking requirements. At the same time, the connector 3 can be completely pulled apart after the stent is deployed, so that the connector 3 is wound around the outer wall of the stent 5 along a predetermined direction, thereby avoiding the occurrence of too many floating lines that affect blood flow. The connector 3 under this connection method can be provided in multiple groups along the circumferential direction of the stent 5. Preferably, asFigure 26 As shown, two groups can be set.

[0061] Preferably, the extendable length of the other part of the connecting member 3 is greater than the distance from the proximal end of the stent 5 to the locking groove 21. It can be understood that in this embodiment, one part of the connecting member 3 is connected to the proximal end of the compressed stent 5, and the remaining other part forms a free end. The other part is used to be sleeved and locked in the locking groove 21 of the anchor 2, and the length of this part needs to be at least greater than the distance from the proximal end of the stent 5 to the locking groove 21 to ensure that the other part of the connecting member 3 can be sleeved in the locking groove 21. In an implemented embodiment, taking the stent 5 with an expected diameter of 2.7 mm in the unexpanded state and expanded to a diameter of 10 mm in the expanded state as an example, assuming the distance from the proximal end of the stent 5 to the locking groove 21 is L0, then L0 needs to satisfy L0 < (L - 2.7 * π) / 2.

[0062] Embodiment Three:

[0063] In this embodiment, please refer to Figure 12 and Figure 13 , the structure of the anchor 2 is substantially the same as that in Embodiment One and Embodiment Two. The difference is that a wire groove 24 is provided on the circumferential side of the side wall of the anchor 2 close to the locking groove 21. One end of the wire groove 24 is connected to the circumferential side of the locking groove 21, and the other end penetrates through the distal end face of the anchor 2. The wire groove 24 is used to accommodate the connecting member 3 sleeved on the anchor 2 when the anchor 2 is in the locked state. When the connecting member 3 is sleeved on the anchor 2, the two sides of the connecting member 3 after sleeving are accommodated in the wire groove 24, which can prevent the connecting member 3 from rubbing against the sheath or the blood vessel wall when the transporter enters the blood vessel in the human body, damaging the blood vessel wall or the sheath, and at the same time can also effectively avoid the random swing of the connecting member 3 from affecting the passing size of the transporter during transportation. Preferably, taking the wire diameter of the connecting member 3 as 0.3 mm as an example, the circumferential width H1 of the wire groove 24 is 0.5 - 0.7 mm; further preferably, in order to avoid the connecting member 3 after accommodation protruding from the surface of the wire groove 24 and causing an impact, the depth of the wire groove 24 needs to be greater than or equal to the wire diameter of the connecting member 3. Taking the wire diameter of the connecting member 3 as 0.3 mm as an example, the radial depth H2 of the wire groove 24 is 0.3 - 0.7 mm; and in order to avoid the corners of the locking groove 21 and the wire groove 24 of the anchor 2 being too sharp, there is a risk of damaging the blood vessel wall or a risk of fracture due to friction with the connecting member 3, preferably, the edges of the wire groove 24 and the locking groove 21 are both provided with rounded corners for transition; using rounded corners for transition can further effectively avoid the risk of the locking groove 21 hanging up on the connecting member 3 when the transporter is withdrawn and released in the unlocked state of the anchor 2. The rounded corner design can provide a certain smoothness when hanging up occurs, thereby avoiding the occurrence of hanging up.

[0064] Further preferably, please refer to Figure 13, between one side wall of the locking groove 21 close to the distal end in the axial direction and the adjacent second core-passing part 26, an arc surface transition can be adopted, and the core-passing hole 23 is arranged on this arc surface. In this way, when the anchor 2 is in the unlocked state and the conveyor is retracted and released, the risk that the locking groove 21 catches the connecting piece 3 can be avoided by bending, which is beneficial to the connecting piece 3 directly sliding out of the locking groove 21 and being released after the lock core 7 is unlocked.

[0065] Embodiment 4:

[0066] In this embodiment, please refer to Figure 14 , the structure of the conveyor is substantially the same as that in Embodiments 1 to 3. The difference is that a locking assembly 8 is connected to the proximal end of the lock core 7, and the locking assembly 8 is threadedly connected to the pipe orifice of the core wire pipeline 61; the locking assembly 8 includes an operating handle 81 and a locking nut structure 82 arranged at the front end of the operating handle 81. An external thread is arranged at the pipe orifice position of the core wire pipeline 61, and the locking nut structure 82 can be threadedly engaged with the external thread of the pipe orifice, so as to realize tightening and locking, and fixedly connect the lock core 7 with the operating handle 81, which can prevent the lock core 7 from being accidentally pulled, resulting in the destruction of the locking structure between the distal end of the lock core 7 and the anchor 2; when the stent 5 is conveyed to the designated blood vessel position and the operator needs to pull the lock core 7, the operator can unscrew the connection between the locking nut structure 82 and the external thread of the pipe orifice of the core wire pipeline 61, and then can retract and pull the operating handle 81 to pull the lock core 7 out of the second core-passing part 26 to release the lock, and the stent 5 is freely released.

[0067] Preferably, the front end of the lock core 7 and the locking assembly 8 satisfy that when the locking assembly 8 is threadedly connected and tightened with the pipe orifice of the core wire pipeline 61, the front end of the lock core 7 is inserted into the second core-passing part 26.

[0068] Further preferably, in order to facilitate the sliding of the lock core 7 in the first lumen 11 and reduce the frictional resistance between the lock core 7 and the inner cavities of the first lumen 11 and the core wire pipeline 61 when pulling the lock core 7 from the base 6 end, the surface of the lock core 7 is covered with a lubricating coating, and the lubricating coating is one of a PTFE coating or a parylene coating, preferably a PTFE coating.

[0069] In an implemented example, the lock core 7 is made of a solid metal wire with a diameter of 0.3 to 0.4 mm, preferably a nitinol wire.

[0070] Embodiment 5:

[0071] In this embodiment, please refer to Figure 15, the structure of the conveyor is generally the same as that in the first to fourth embodiments. The difference is that the conveyor in this embodiment is a balloon catheter. A balloon body 41 is provided on the stent loading area 4 of the balloon catheter. Both ends of the balloon body 41 are fixedly connected to the outer wall of the tube body 1 by bonding or welding to form a closed internal space. Among them, the stent 5 is provided on the balloon body 41 and is expanded by the expansion of the balloon body 41. The tube body 1 further includes a second lumen 13, and the base 6 includes a balloon pressurization pipeline. One end of the second lumen 13 communicates with the balloon pressurization pipeline 62, and the other end communicates with the inner cavity of the balloon body 41. The second lumen 13 is used for balloon pressurization, and the pressurization medium can be gas or liquid.

[0072] In this embodiment, when the conveyor is a balloon catheter, the tube body 1 has a three-lumen tube structure in which the first lumen 11, the second lumen 13, and the third lumen 12 are isolated and spaced apart. It should be noted that the tube body 1 is not entirely a three-lumen tube structure. The first tube section 101 has the first lumen 11 and is a three-lumen tube structure, while the second tube section 102 does not have the first lumen 11 and is a two-lumen tube structure.

[0073] Taking the conveyor as a balloon catheter and one end of the connecting member 3 being fixed to the anchoring member 2 as an example, combined with Figures 15 - 18 the working principle of the stent delivery system 100 provided in this embodiment will be introduced:

[0074] Step 1: Before installing the stent 5, screw out the locking nut structure 82 from the nozzle of the core wire pipeline 61 through the operating handle 81, then retract the lock core 7 so that the distal end of the lock core 7 slides out of the second core wire passing part 26, and the lock groove 21 is in the unlocked state. When the stent 5 is pressed and held onto the balloon for installation outside the body, the connecting member 3 on the anchoring member 2 passes through the metal skeleton at the proximal end of the stent 5 and then winds back and hangs in the lock groove 21 of the anchoring member 2. At this time, push the operating handle 81 to make the distal end of the lock core 7 penetrate into the second core wire passing part 26, and the lock groove 21 is in the locked state. Push the balloon catheter along the guide wire into the blood vessel. Since the stent 5 has been hooked and anchored to the anchoring member 2, the stent 5 will not fall off and enter the patient's body during the delivery process.

[0075] Step 2: When the stent 5 reaches the designated delivery position, screw out the locking nut structure 82 from the nozzle of the core wire pipeline 61 again through the operating handle 81, then retract the lock core 7 so that the distal end of the lock core 7 slides out of the second core wire passing part 26, and the lock groove 21 is in the unlocked state. At this time, fill the balloon with the pressurization medium through the balloon pressurization pipeline, and the balloon expands to drive the stent 5 to expand and release.

[0076] Step 3: After the release is completed, extract the pressurization medium in the balloon to make the balloon contract and fold, and then retract the balloon catheter to disconnect the connecting member 3 from the stent 5.

[0077] Embodiment Six:

[0078] See also Figure 19 In this embodiment, the structure of the stent delivery system 100 is substantially the same as that of the first to fifth embodiments, except that the base 6 may not be provided with a core wire pipeline and an operating handle, so that the lock core 7 may not extend to the proximal base 6 to control its entry and exit in the lock groove 21 of the anchor by the operating handle. In order to enable the stent delivery system to hook the stent 5 to prevent slipping when delivering the stent 5, and to automatically release the hook of the connector 3 when the balloon is expanded, specifically, a fixing member 9 may be provided on the proximal surface of the balloon body 41, and one end of the lock core 7 is connected to the fixing member 9 for fixing. Here, the fixing member 9 may be connected only to a portion of the surface of the balloon body 41 to ensure that the balloon body 41 is connected except for the connection of the fixing member 9. Other positions outside the position can be expanded by the stamping pipeline to support and release the bracket 5; after the lock core 7 is connected, the other end extends to the distal end of the anchor and penetrates into the through hole of the anchor, here, the through hole of the anchor axially penetrates the two ends of the anchor axially, and the axial lengths of the first through hole and the second through hole are equal, so that the lock core 7 of the anchor can be penetrated from the proximal and distal ends of the anchor to pass through the two side walls of the lock groove 21, thereby realizing the connection and locking of the connector 3. At the same time, the lock core 7 of the anchor props up the lock core 7 after the balloon is expanded, so that the lock core 7 is detached from the proximal side wall of the lock groove 21, and as the lock core 7 is continuously propped up, the connector 3 is detached from the proximal free end of the lock core 7, thereby realizing the unlocking of the connector 3.

[0079] In this example, see Figures 19 - 20 The fixing member 9 is elastic, and specifically can be an elastic polymer ring, such as a polyester material; the polymer ring can be bonded or welded to the surface of the balloon body 41 along the circumference of the balloon body 41, and expand and contract synchronously with the expansion and contraction of the balloon body 41; the nickel-titanium wire can also be an elastic polymer rod, and the lock core 7 is configured to have an elastic force to press the end away from the fixing member 9 toward the tube body in a natural state or a stressed state, thereby preventing the lock core 7 from shaking or deviating at will and affecting the blood vessels; wherein the balloon body 41 includes a first state of radial contraction and a second state of radial expansion. When the balloon body 41 is in the first state , the lock core 7 passes through the two axial side walls of the lock groove 21 at the same time. At this time, the connecting piece 3 is at least partially arranged in the lock groove 21 and is hooked by the lock core 7, which can prevent the stent 5 from slipping off the balloon body 41 and falling into the blood vessel to cause danger; when the balloon body 41 is in the second state, the balloon body 41 is punched and expanded, and the stent 5 is expanded and expanded. At the same time, the radial position of the fixing piece 9 on the surface of the balloon body 41 relative to the tube body is raised, thereby pulling the lock core 7 out of the lock groove 21, so that the lock core 7 does not pass through the lock groove 21. At this time, the connecting piece 3 can be moved out of the lock groove 21 to release the hook with the anchor, and the stent 5 is released to the specified position, and the stent 5 will not be pulled when the tube body is withdrawn.

[0080] In one embodiment, see Figure 21 When the balloon body 41 is in the second state, the lock core 7 is pulled out from the lock groove 21 and at least detached from the proximal side wall of the lock groove 21, and the head end of the lock core 7 away from the fixing member 9 is placed in the core-penetrating portion; in this way, after the stent 5 is released, the tube body can be further prevented from being placed and swung arbitrarily during the withdrawal process, thereby preventing the head end of the lock core 7 from affecting the inner wall of the blood vessel.

[0081] In another embodiment, when the connector 3 is disposed at the proximal end of the stent 5, as the balloon 41 expands, the connector 3 is automatically pulled back by the stent 5 and wrapped around the surface of the stent 5 as the stent 5 expands, thereby forming a structure for the connector 3 to automatically withdraw from the locking groove 21, thereby effectively avoiding the possibility of the anchor member hooking the connector 3 when the tube body is withdrawn.

[0082] In some embodiments, see Figure 22 The locking groove 21 of the anchor has an arc-shaped transition to the opening of the through hole on the side wall away from the balloon body 41, so that when the balloon body 41 releases the pressure and retracts after completing the expansion and release of the stent 5, it is convenient for the end of the lock core 7 away from the fixing member 9 to better penetrate into the through hole part of the anchor away from the balloon body 41, thereby avoiding the lock core 7 from scratching or puncturing the blood vessel during withdrawal.

[0083] In this embodiment, the lock core 7 is connected to the balloon body 41 by means of a fixing member 9, which can effectively reduce the length of the lock core 7 and reduce the steps for controlling the lock core 7 during the operation, thereby effectively avoiding the problem of the lock core 7 being difficult to control due to excessive friction when the lock core 7 is passed along the tube body, and at the same time, it can also reduce the surgical steps to improve the surgical efficiency.

[0084] In other embodiments, see Figures 22 - 23 In order to further ensure that the balloon body 41 can avoid the risk of the connector 3 being disengaged from the lock groove 21 and unlocked during the process of punching and releasing the stent 5, causing the stent 5 to lose its hook in advance, specifically, the axial length L2 of the lock core 7 satisfies: when the balloon body 41 expands to the maximum balloon diameter, the proximal end of the lock core 7 away from the fixing member is at least flush with the distal side wall 211 of the lock groove 21, or is received in the distal side wall 211 of the anchor 2, that is, the balloon has a radius R1 when it expands to the maximum balloon diameter, and the distance between the fixing member 9 and the distal side wall 211 of the anchor 2 is L3, satisfying R12+L3 2≤L22; and, when the connecting member 3 is in a tensile state, half of the total length L1 is less than or equal to the axial length L2 of the lock core 7, and the connecting member 3 is elastic. With such a setting, during the expansion process of the balloon body 41, the stent 5 expands along with the expansion of the balloon body 41. The balloon body 41 expands preferentially, and the expansion of the stent 5 is subsequent. Thus, when the balloon body 41 is not expanded to the maximum diameter, since half of L1 is less than the axial length L2 of the lock core 7, L1 reaches the distal side wall 211 of the lock groove 21 prior to the proximal side end of the lock core 7 away from the fixing member. And at this time, since the proximal side end of the lock core 7 away from the fixing member does not reach the distal side wall 211, there is still a continuous hooking effect on the connecting member 3 until the proximal side end of the lock core 7 away from the fixing member is flush with the distal side wall 211 of the anchoring member 2. At the same time as the stent 5 is completely expanded and released, the hooking of the connecting member is released, completing the unlocking and releasing process of the entire stent 5.

[0085] Embodiment Seven:

[0086] In order to further ensure that the connecting member 3 can be disengaged and to increase the disengagement speed of the connecting member 3, a preferred solution is further proposed in this embodiment on the basis of Embodiment Six. It should be understood that some structures can refer to Embodiment Six and will not be elaborated here. Only the differences from Embodiment Six will be described in detail here.

[0087] Referring to Figures 24 - 26 , the anchoring member 2 includes an anchoring co - connecting portion 2a extending along the entire axial length of the anchoring member 2, a distal anchoring portion 2b located on the distal side, and a proximal anchoring portion 2c located on the proximal side. The distal anchoring portion 2b and the proximal anchoring portion 2c are axially spaced apart, and the lock groove 21 is formed at the spaced - apart portion therebetween. Among them, the distal anchoring portion 2b and the proximal anchoring portion 2c are provided with coaxial distal core - passing holes 231 and proximal core - passing holes 232.

[0088] In this embodiment, a local axial portion at the proximal end of the proximal anchoring portion 2c extends toward the distal end to form a proximal anchoring extension portion 2c1. The proximal anchoring extension portion 2c1 is located at the side of the axis of the core - passing hole 23. A wire - passing hole 2c11 is provided in the proximal anchoring extension portion 2c1 in the radial direction. The connecting member 3 can pass through the wire - passing hole 2c11 so that the loop - shaped connecting portion 3a on the connecting member 3 is hooked on the lock core 7. In this way, the wire - passing hole 2c11 forms a limit on the connecting member 3. When the lock core 7 disengages from the proximal core - passing hole 232 on the proximal anchoring portion 2c, the connecting member 3 is limited, and the distance it moves axially along with the lock core 7 is limited, enabling the connecting member 3 to quickly disengage from the lock core 7 to achieve unlocking, and at the same time, the lock core 7 does not need to move too long axially.

[0089] Continuing to refer to Figures 24 - 26, in order to prevent the lock core 7 from disengaging from the distal through-hole 231 of the distal anchoring portion 2b as the balloon body 41 expands, which may affect the retraction of the delivery device. In other embodiments, as Figure 25 shown, a stepped portion 2b1 is formed in the distal through-hole 231 of the distal anchoring portion 2b. For example, the distal through-hole 231 includes a large hole at the proximal end and a small hole at the distal end that are coaxially arranged, and the stepped portion 2b1 is formed between the large hole and the small hole. An elastic member m is disposed in the distal through-hole 231, the elastic member m is sleeved on the lock core 7, a blocking portion 71 is provided on the outer peripheral side of the lock core 7, the distal end of the elastic member m abuts against and is relatively fixed to the stepped portion 2b1, and the proximal end of the elastic member m abuts against the blocking portion 71. In the natural state, the loop-shaped connecting portion 3a of the connecting member 3 passes through the wire passing hole 2c11 and is hooked on the lock core 7, and in this state, the elastic member m is in an unfolded state, so that the proximal end of the lock core 7 always extends into the proximal through-hole 232 under the action of the elastic force, ensuring the stability of the locking and preventing the lock core 7 from being disengaged and released randomly.

[0090] As the balloon body 41 expands, the force provided by the expansion is greater than the elastic force of the elastic member m, so that the lock core 7 is continuously lifted, and the proximal end of the lock core 7 continuously moves toward the distal side. At this time, the elastic member m will be continuously compressed, and then the loop-shaped connecting portion 3a of the connecting member 3 disengages from the lock core 7. As the elastic member m is continuously squeezed, the lock core 7 stops moving after moving to the maximum range; when the balloon body 41 is depressurized, the proximal end of the lock core 7 moves toward the proximal side under the elastic force of the elastic member 7, and finally the free end of the proximal end of the lock core 7 enters the proximal through-hole 232 again.

[0091] In other embodiments, as Figure 25 and Figure 26 shown, the proximal through-hole 232 is in the shape of a horn that is large at the proximal end and small at the distal end, which is convenient for the free end of the proximal end of the lock core 7 to enter the proximal through-hole 232 smoothly again. In order to improve the locking property, an elastic sleeve n is sleeved in the proximal through-hole 232. The shape of the elastic sleeve n can be adapted to the proximal through-hole 232. After the elastic sleeve n is sleeved in the proximal through-hole 232, it is fixed to the proximal anchoring portion 2c through a bottom locking member. The elastic sleeve n can elastically abut against the free end of the proximal end of the lock core 7 extending into it, thereby improving the stability and locking property of the lock core 7. The above is only a preferred specific embodiment of the present invention, but the protection scope of the present invention is not limited thereto. Any changes or substitutions that can be easily thought of by those skilled in the art within the technical scope disclosed by the present invention should be covered by the protection scope of the present invention; therefore, the protection scope of the present invention should be subject to the protection scope of the claims.

Claims

1. A stent delivery system, characterized in that: The invention comprises a tube body, a connecting piece and a stent loading area arranged at the distal end of the tube body, wherein the stent loading area is used to load the stent, and an anchor is sleeved on a tube section of the tube body close to the stent loading area; the anchor is configured to have a locked state and an unlocked state, and the connecting piece is configured to simultaneously connect the anchor and the stent when the anchor is in the locked state; When the anchor is in the unlocked state, the connector is disconnected from the anchor or the bracket.

2. The stent delivery system according to claim 1, characterized in that: The anchor member includes a lock core, and a lock groove is provided on the circumferential side wall of the anchor member. The anchor member is provided with a through hole in the axial direction, and the through hole passes through the two axial side walls of the lock groove. The lock core is passed through the through hole and can slide axially along the through hole; when the lock core passes through the two axial side walls of the lock groove at the same time, the anchor member is in a locked state.

3. The stent delivery system according to claim 2, characterized in that: The connecting member is flexible and comprises a folded back connecting portion. When the anchoring member is in a locked state, the folded back connecting portion is sleeved on the lock core in the lock groove.

4. The stent delivery system according to claim 3, characterized in that: The connecting member includes a fixed end and a free end, and the fixed end is fixedly connected to the distal end of the anchor member; the free end includes the circular connecting portion, and when the anchor member is in a locked state, the free end hooks the bracket and the circular connecting portion is sleeved on the lock core in the lock slot.

5. The stent delivery system according to claim 3, characterized in that: The connecting member includes a fixed part and a free part, the fixed part is connected to the proximal end of the bracket, and the free part includes the circular connecting portion. When the anchor is in a locked state, the circular connecting portion of the free part is sleeved on the lock core in the lock groove.

6. The stent delivery system according to claim 5, characterized in that: The connector surrounds the proximal end of the stent, and the circumference of the connector is greater than or equal to the circumference of the stent after expansion; or, The connecting piece surrounds a part of the circumference of the proximal end of the stent, and the length of the connecting piece is greater than or equal to the arc length of the corresponding part after the stent is expanded.

7. The stent delivery system according to claim 5, characterized in that: The free portion of the connecting member can extend to a length greater than the distance from the proximal end of the bracket to the locking groove.

8. The stent delivery system according to claim 2, characterized in that: A first lumen is provided in the tube body, and a distal end of the first lumen is connected to the outside world at the distal end side of the tube body close to the anchor. The lock core can slide axially in the first lumen and pass through the distal end, and then pass through the core hole from the proximal end of the anchor.

9. The stent delivery system according to claim 2, characterized in that: The stent loading area includes a balloon body, and the stent can be installed on the balloon body; a fixing piece is provided on the proximal surface of the balloon body, one end of the lock core is connected to the fixing piece, and the other end can extend to the distal end of the anchor and penetrate into the core hole.

10. The stent delivery system according to claim 9, characterized in that: The fixing piece is elastic, and the balloon body includes a first state of radial contraction and a second state of radial expansion. When the balloon body is in the first state, the lock core can simultaneously pass through the two axial side walls of the lock groove; when the balloon body is in the second state, the lock core at least detaches from the proximal side wall of the lock groove.

Images