Lockable implant pushing device and implant delivery system

Abstract

The present invention discloses a lockable implant pushing device and an implant delivery system, wherein the implant delivery system comprises an implant pushing device, an expansion device, a loading device, a hemostatic device and an outer sheath. The pushing device comprises a pushing assembly and a handle assembly connected to the proximal end of the pushing assembly, wherein the pushing assembly comprises a hollow pushing steel cable, an inner core movably inserted into the pushing steel cable, and a clamping member provided at the distal end of the inner core and detachably connected to the implant; the clamping member comprises at least two clamping arms, wherein at least one clamping arm is provided with a hook at the distal end, wherein the hook extends toward or away from the central axis of the pushing steel cable, and the extension directions of the multiple hooks are different. The present invention has a reliable connection with the implant, preventing the implant from being released prematurely before reaching the designated location, and can be released by a single-handed operation to release the implant.

Description

Technical Field

[0001] The invention belongs to the technical field of medical devices and relates to a lockable implant pushing device and an implant delivery system. Background Art

[0002] In recent years, interventional therapy has been widely used in clinical applications. Interventional therapy refers to the use of catheter technology to place various materials, instruments, etc. into the heart, arteries, veins and other parts of the human body to treat cardiovascular diseases. For example, a vena cava filter (abbreviated as: VCF) is placed in the patient's superior and inferior vena cava through catheter intervention to capture detached thrombi and prevent the thrombi from moving up along the vena cava system to the heart and lungs, causing pulmonary embolism; or a left atrial appendage occluder is delivered to the left atrial appendage to prevent thrombi caused by atrial fibrillation from ascending to the brain, causing stroke or other systemic embolism. The implantation of such devices requires a delivery system to deliver the implant to various parts of the human body, and then separate the push device from the implant. The current connection method between the push device and the implant is mainly threaded connection or connection relying solely on the friction of the implant itself. The main disadvantages of this type of push device and delivery system are: 1. The structure is complex. During the delivery or release process, the push device and the implant need to rotate directly relative to each other. The rotation process is uncontrollable, resulting in inconvenient operation; 2. In curved human blood vessels, when subjected to blood flushing or friction from the curved inner wall of the blood vessel, the friction may be too large or too small, causing the implant to become stuck, or the connection failure may cause the implant to be released prematurely, resulting in surgical failure. Summary of the Invention

[0003] The technical problem to be solved by the present invention is to provide a lockable implant pushing device to address the defects of the prior art, which has a reliable connection and locking force with the implant and prevents the implant from being released prematurely before reaching the designated position.

[0004] Another technical problem to be solved by the present invention is to provide an implant delivery system which is reliably connected to the implant to prevent the implant from being released prematurely before reaching the designated location, and which can be operated with one hand without rotating the pushing device during release.

[0005] The technical solution adopted by the present invention to solve its technical problem is:

[0006] An implant pushing device comprises a pushing assembly and a handle assembly connected to the proximal end of the pushing assembly, the pushing assembly comprising a hollow pushing steel cable, an inner core movably inserted into the pushing steel cable, and a clamping member provided at the distal end of the inner core and detachably connected to the implant; the clamping member comprises at least two clamping arms, at least one of the clamping arms having a hook provided at its distal end, the hook extending toward or away from the central axis of the pushing steel cable, and the extension directions of the plurality of hooks being different.

[0007] Furthermore, the planes where the ends of at least two of the hooks are located do not overlap.

[0008] Furthermore, the clamping member has a free state and a locked state. When the clamping member is in the free state, the distal end of the clamping arm extends out of the distal end of the push steel cable, and all the distal ends of the clamping arms radiate radially in different directions; when the clamping member is in the locked state, all the clamping arms retract into the push steel cable and converge toward the central axis of the push steel cable, and at least one of the hooks is connected to or interlaced with the clamping arm to form an annular closed structure, or at least two of the hooks are connected to or interlaced to form an annular closed structure.

[0009] Furthermore, in the free state, the angle between at least one of the clamping arms and the central axis of the push steel cable ranges from 90° to 150° or from 200° to 270°, and the angles between the two clamping arms forming an annular closed structure and the central axis of the push steel cable are not equal.

[0010] Furthermore, a limiting piece is provided at the distal end of the pushing steel cable, and a limiting hole is provided along the axial direction of the pushing steel cable. When the clamping piece is in a free state, the hook piece and the distal end of the clamping arm both extend from the limiting hole. When the clamping piece is in a locked state, the hook piece is located outside the limiting hole, and the distal end of the clamping arm connected to the proximal end of the hook piece is closed together in the limiting hole.

[0011] Furthermore, the major axis dimension of the limiting hole is larger than the dimension of the outermost side of each clamping arm of the clamping member in a locked state on a plane perpendicular to the axial direction of the inner core, and smaller than the dimension of each hook of the clamping member in a locked state on a plane perpendicular to the axial direction of the inner core; the minor axis dimension of the limiting hole is approximately equal to the sum of the dimensions of the proximal ends of multiple clamping arms on a plane perpendicular to the axial direction of the inner core.

[0012] Furthermore, the handle assembly includes a handle and an axial drive control mechanism provided on the handle, and the axial drive control mechanism moves axially relative to the handle to drive the axial relative movement between the push cable and the inner core.

[0013] Furthermore, a control groove is provided on the handle along the axial direction, and the axial drive control mechanism moves axially in the control groove.

[0014] Furthermore, the handle assembly also includes an elastic member provided at the proximal or distal end of the axial drive control mechanism, and compression or resetting of the elastic member drives the axial movement of the axial drive control mechanism to drive the axial relative movement between the push cable and the inner core.

[0015] Furthermore, the distal end of the axial drive control mechanism is connected to the push cable, and the proximal end of the axial drive control mechanism is connected to the elastic member.

[0016] Furthermore, the handle is provided with at least two latching positions, which are radially offset relative to the control groove and communicated with the control groove, and the axial drive control mechanism moves in the control groove and the latching positions.

[0017] Furthermore, the locking position includes a first locking position located at the distal end and a second locking position located at the proximal end. When the axial drive control mechanism switches between the first locking position and the second locking position, the clamping member switches between a locked state and a free state.

[0018] Furthermore, the axial drive control mechanism is connected to the push cable, and when the axial drive control mechanism is located in the first clamping position, the clamping member is in a locked state; when the axial drive control mechanism is located in the second clamping position, the clamping member is in a free state.

[0019] An implant delivery system comprises the aforementioned implant pushing device and an outer sheath tube with a certain axial length. The implant pushing device is movably installed in the outer sheath tube and is detachably connected to the proximal end of the outer sheath tube.

[0020] Furthermore, the implant delivery system further comprises an expansion device, which is movably installed in the outer sheath, and the proximal end of the expansion device is detachably connected to the proximal end of the outer sheath.

[0021] Furthermore, the implant delivery system further comprises a loading device, which is detachably connected between the proximal end of the outer sheath and the distal end of the pushing device.

[0022] Furthermore, the implant delivery system further comprises a hemostatic device, which is detachably connected between the loading device and the distal end of the pushing device.

[0023] Furthermore, at least one of the outer sheath, the loading device and the hemostasis device is provided with an elastic sealing member, and the elastic sealing member is provided with at least one aperture along the axial direction of the pushing device.

[0024] Furthermore, a first slit is formed at the proximal end of the elastic seal, and a second slit is formed at the distal end of the elastic seal, the sum of the thicknesses of the first slit and the second slit is equal to the thickness of the elastic seal, the directions of the first slit and the second slit are different, and the projection of the first slit on the distal surface of the elastic seal intersects with the projection of the second slit on the distal surface of the elastic seal.

[0025] Furthermore, the projection of the first slit on the distal end surface of the elastic seal is perpendicular to the projection of the second slit on the distal end surface of the elastic seal.

[0026] Compared with the prior art, the present invention has at least the following beneficial effects:

[0027] The hooks of the implant pushing device are connected or overlapped to form a ring-shaped closed structure, which can lock the connection with the implant and prevent the implant from being released prematurely before reaching the designated position; furthermore, the opening shape of the clamping piece and the size of the locking force can be adjusted according to different implant types and the implant's requirements for the connection force of the pushing device, and the application range is wide.

[0028] When releasing the implant, the operator does not need to rotate the pushing device. Instead, they can simply operate the axial drive control mechanism and elastic member on the handle with one hand. The compression or reset of the elastic member drives the axial movement of the axial drive control mechanism to quickly release the implant, making the operation convenient and simple. Alternatively, the operator can operate the axial drive control mechanism on the handle with one hand to control the axial drive control mechanism to move within the control slot and the locking position, thereby quickly releasing the implant, making the operation convenient and simple. BRIEF DESCRIPTION OF THE DRAWINGS

[0029] The present invention will be further described below with reference to the accompanying drawings and embodiments, in which:

[0030] Figure 1 1 is a partial cross-sectional view of an implant pushing device according to a first embodiment of the present invention, wherein the implant pushing device includes a pushing assembly and a handle assembly;

[0031] Figure 2 yes Figure 1 Exploded view of the push assembly, which includes a push cable, an inner core, a clamping member, and a limit member;

[0032] Figure 3 yes Figure 1 A schematic structural diagram of the clamping member in FIG.

[0033] Figures 4a-4d Schematic diagrams of the structures of different embodiments of the clamping member;

[0034] Figure 5a-5b yes Figure 1 Schematic diagram of different states of the clamping member in FIG, wherein: Figure 5a The clamp is in a free state. Figure 5b The clamping member is in a locked state;

[0035] Figure 6 yes Figure 1 A schematic diagram of the structure of the limiting member in FIG.

[0036] Figure 7 yes Figure 1 Schematic diagram of the connection between the clamp and the implant;

[0037] Figure 8 yes Figure 1 a cross-sectional view of the handle assembly in FIG.

[0038] Figure 9 1 is a schematic structural diagram of a clamping member of an implant pushing device according to a second embodiment of the present invention;

[0039] Figure 10 yes Figure 9 A schematic diagram of the structure when the clamping member is in a free state;

[0040] Figure 11 yes Figure 9 A schematic diagram of the structure when the clamping member is in a locked state;

[0041] Figure 12 1 is a schematic structural diagram of a clamping member of an implant pushing device according to a third embodiment of the present invention;

[0042] Figure 13 yes Figure 12 A schematic diagram of the structure when the clamping member is in a free state;

[0043] Figure 14 yes Figure 12 A schematic diagram of the structure when the clamping member is in a locked state;

[0044] Figure 15 1 is a schematic structural diagram of an implant pushing device according to a fourth embodiment of the present invention;

[0045] Figure 16a and Figure 16b yes Figure 15 A partial cross-sectional view of Figure 16a The clamp is in a free state. Figure 16b The clamping member is in a locked state;

[0046] Figure 17 yes Figure 15 Exploded view of the handle assembly in;

[0047] Figure 18 is a partial cross-sectional view of an implant pushing device according to a fifth embodiment of the present invention;

[0048] Figure 19 yes Figure 18 Exploded view of the handle assembly in;

[0049] Figure 202 is a schematic structural diagram of an implant delivery system according to a sixth embodiment of the present invention, wherein the implant delivery system includes an implant pushing device, an expansion device, a loading device, a hemostatic device, and an outer sheath;

[0050] Figure 21 yes Figure 20 Schematic diagram of the outer sheath and dilation device assembled together;

[0051] Figure 22 yes Figure 20 Schematic diagram of the loading device, hemostasis device and pushing device assembled together;

[0052] Figure 23 yes Figure 20 Schematic diagram of the outer sheath, loading device, hemostasis device and pushing device assembled together;

[0053] Figure 24 yes Figure 20 Schematic diagram of the structure of the outer sheath;

[0054] Figure 25 yes Figure 24 A partial cross-sectional view of the sheath tube seat;

[0055] Figure 26 yes Figure 25 A schematic diagram of the structure of the elastic seal;

[0056] Figure 27a yes Figure 26 Cross-sectional view along BB;

[0057] Figure 27b yes Figure 26 Cross-sectional view along CC.

[0058] Figure 28 yes Figure 20 A schematic structural diagram of the expansion device in FIG.

[0059] Figure 29 yes Figure 20 A schematic structural diagram of the loading device in FIG.

[0060] Figure 30 yes Figure 20 Schematic diagram of the structure of the hemostatic device. DETAILED DESCRIPTION

[0061] In order to have a clearer understanding of the technical features, purposes and effects of the present invention, specific embodiments of the present invention are now described in detail with reference to the accompanying drawings.

[0062] Definition of orientation: In the field of interventional medicine, the end closer to the operator during surgery is usually called the "proximal end" and the end farther from the operator is called the "distal end".

[0063] Example 1

[0064] See also Figures 1 to 7 The implant pushing device 10 of the first embodiment is used to push the implant 200 to a predetermined position in the patient's body and release it. The implant 200 includes but is not limited to a vascular filter, a vascular stent, a heart valve clamp, a heart defect occluder, a vascular plug or a lung volume reduction elastomer. The implant 200 is made of a material with shape memory function and can be stretched into a linear shape and loaded into a hollow tube body when used. The proximal end of the implant 200 is provided with a connecting portion, usually a curved retrieval hook or at least one through hole, for forming a detachable connection with the implant pushing device 10. In this embodiment, the implant 200 is an inferior vena cava filter, and the proximal end of the inferior vena cava filter is provided with a curved retrieval hook. The implant pushing device 10 delivers the inferior vena cava filter to the patient's inferior vena cava and releases it.

[0065] The implant pushing device 10 includes a pushing assembly 1000 and a handle assembly 2000 connected to the proximal end of the pushing assembly 1000. Figure 2 and Figure 3 The pushing assembly 1000 includes a hollow pushing cable 1100, an inner core 1200 movably inserted into the pushing cable 1100, and a clamping member 1300 disposed at the distal end of the inner core 1200 and detachably connected to the implant 200. Figures 4a to 4d The clamping member 1300 includes at least two clamping arms 1320, and a hook 1310 is provided at the distal end of at least one clamping arm 1320. The hook 1310 extends toward or away from the central axis of the push cable 1100. The extension directions of the multiple hooks 1310 are different, and the planes of at least two hooks 1310 do not overlap.

[0066] See also Figure 5a and Figure 5b The clamping member 1300 has a free state and a locked state. When the clamping member 1300 is in the free state, the distal end of the clamping arm 1320 extends out of the distal end of the push cable 1100, and the distal ends of all the clamping arms 1320 radiate in different directions along the radial direction; when the clamping member 1300 is in the locked state, all the clamping arms 1320 retract into the push cable 1100 and converge toward the central axis of the push cable 1100, and at least one hook 1310 is connected to or interlaced with the clamping arm 1320 to form an annular closed structure, or at least two hooks 1310 are connected to or interlaced to form an annular closed structure. Figure 10When only one hook 1310 is provided at the distal end of one clamping arm 1320, the hook 1310 cooperates with the other clamping arms 1320 to form a ring-shaped closed structure. When hooks 1310 are provided at the distal ends of multiple clamping arms 1320, each hook 1310 can cooperate with the other clamping arms 1320 to form a ring-shaped closed structure, and each hook 1310 can also cooperate with the other hooks 1310 to form a ring-shaped closed structure.

[0067] In the present invention, the hook 1310 extending toward the central axis of the push cable 1100 means that the end of the hook 1310 is toward the central axis of the push cable 1100, and the hook 1310 extending away from the central axis of the push cable 1100 means that the end of the hook 1310 is away from the central axis of the push cable 1100. The hooks 1310 are connected, which means that the end faces of at least two hooks 1310 are in contact and pressed, or the end faces of the hooks 1310 are in contact and pressed with the end faces of the clamping arms 1320, forming an annular closed structure. The hooks 1310 are staggered, which means that the hooks 1310 at least cross each other at their ends to form an annular closed structure, or that the ends of the hooks 1310 do not touch but their radial projections on the same plane overlap, or that multiple hooks 1310 at least have a section of their ends in contact with each other to form an annular closed structure. Likewise, when one hook 1310 is provided, the end of the hook 1310 or the hook 1310 and the clamping arm 1320 intersect and cross to form a ring-shaped closed structure.

[0068] See again Figure 2 The push cable 1100 is made of a material with certain flexibility and support, and its cross-section can be a smooth structure such as a circle or a semicircle, preferably a circle. The flexibility here means that the push cable 1100 can be bent or twisted to a certain extent, and the push cable 1100 is usually made of a biocompatible metal material or a polymer material. The preferred metal materials are: 316 stainless steel, 304 stainless steel, and the polymer materials are: nylon, polyethylene, and Pebax. In this embodiment, the push cable 1100 is a hollow tube with a smooth inner wall, which is twisted from three strands of steel wire. In order to strengthen the support of the push cable 1100, a steel wire can be wrapped around the outside of the twisted multiple strands of steel wire (not shown in the figure). It can be understood that in other embodiments, in order to enhance the smoothness and support of the push cable 1100, the push cable 1100 is covered with a coating or a metal reinforcement tube; the coating is made of a biocompatible polymer material, preferably PTFE, e-PTFE or Pebax.

[0069] The inner core 1200 is of a certain length and is more flexible than the push cable 1100. The inner core 1200 is generally a single metal wire (such as a steel wire or a nickel-titanium wire). The inner core 1200 is movably installed in the push cable 1100, which means that the inner core 1200 and the push cable 1100 can move relative to each other along the axial direction and can also rotate relative to each other.

[0070] like Figure 3 As shown, the clamping member 1300 is arranged at the distal end of the inner core 1200. The clamping member 1300 and the inner core 1200 can be formed as one piece, or they can be formed separately and then fixed together. In this embodiment, the proximal end of the clamping member 1300 is provided with a clamping connection portion 1330 for connecting to the inner core 1200. The connection between the clamping connection portion 1330 and the inner core 1200 can be a detachable fixed connection such as a threaded connection, a snap-fit, an interference fit, or a non-detachable fixed connection such as a riveting, welding, or hot pressing. In this embodiment, the clamping member 1300 is welded to the distal end of the inner core 1200 to simplify the device structure and improve the connection firmness and device reliability. The clamping connection portion 1330 and the clamping arm 1320 can be made of the same material or different materials. Preferably, to ensure proximal support of the clamping member 1300, the clamping connection portion 1330 is a supporting tubular or rod-shaped structure made of a relatively rigid material, preferably 316 stainless steel, 304 stainless steel, nickel-titanium alloy, or cobalt-chromium alloy. In this embodiment, the clamping connection portion 1330 and the clamping arm 1320 are both made of stainless steel and are integrally formed.

[0071] The clamping member 1300 includes two clamping arms 1320, each of which is provided with a hook 1310 at its distal end. Each hook 1310 extends toward the central axis of the push cable 1100, and the two hooks 1310 extend in different directions. Thus, the two hooks 1310 intersect to form a ring-shaped closed structure. When the clamping arms 1320 are open, sufficient space is left between the hooks 1310 for the connecting portion of the implant 200 to enter. When the clamping arms 1320 are closed, the ends of the two hooks 1310 approach and intersect to form a ring-shaped closed structure that is connected to the connecting portion of the implant 200. It is understood that in other embodiments, multiple clamping arms 1320 may be provided to strengthen the firmness of the ring-shaped closed structure and improve the connection force. Each clamping arm 1320 is provided with a hook 1310 extending toward the central axis of the pushing steel cable 1100, that is, after the clamping arms 1320 are closed, the ends of all the hooks 1310 are connected or intertwined at or near the central axis of the pushing steel cable 1100, together forming an annular closed structure.

[0072] When the clamping member 1300 is in a free state, the clamping arm 1320 is selected from at least one of a straight rod structure, a broken line rod structure, and a curved rod structure. In this embodiment, the clamping arm 1320 is a hollow or solid straight rod structure.

[0073] When the clamping member 1300 is in a free state, the distal ends of the clamping arms 1320 radiate radially in different directions, that is, the proximal ends of the multiple clamping arms 1320 are concentrated, and the distal ends are spread out. In the free state, the angle α between at least one clamping arm 1320 and the central axis of the push cable 1100 is preferably in the range of 90° to 150° or 200° to 270°, that is, 90°≤α≤150° or 200°≤α≤270°, preferably 100°≤α≤130° or 230°≤α≤260°. In order to form an annular closed structure, it is necessary to ensure that two adjacent clamping arms 1320 do not overlap, so the angles α between the two clamping arms 1320 forming the annular closed structure and the central axis of the push cable 1100 are unequal. Preferably, the multiple clamping arms 1320 are symmetrically distributed about the central axis of the push cable 1100. Therefore, when the clamping member 1300 is in a free state, there is always a certain opening angle between at least two clamping arms 1320, and they will not be completely closed, which is more conducive to the clamping arms 1320 being retracted into the push cable 1100 and reducing the contraction force. In this embodiment, the clamping member 1300 includes two clamping arms 1320, and the angles α between the two clamping arms 1320 and the central axis of the push cable 1100 are 120° and 240° respectively, that is, the two clamping arms 1320 are symmetrically arranged about the central axis of the push cable 1100.

[0074] The clamping arm 1320 is formed through a shaping process and is in an extended state when in a free state. To ensure that the clamping arm 1320 can be smoothly retracted after being compressed by the push cable 1100 and can be smoothly extended after being released from the constraint, the clamping arm 1320 of the clamping member 1300 should be made of an elastic material and formed through a shaping process so that the clamping arm 1320 is in an extended state when in a free state. The elastic material here refers to a material that can bend or twist under external force and then return to its original shape. Preferably, it is a shape memory material such as nickel-titanium alloy, stainless steel, or cobalt-chromium alloy.

[0075] The distal end of the clamping arm 1320 is provided with a hook 1310. Figures 4a-4d As shown, the hook 1310 can be one or more short rods extending toward or away from the central axis. The shape of the short rod can be a straight rod structure, a broken line rod structure composed of multiple straight rods, a straight rod structure with bifurcations, or a curved rod structure. Figure 4a As shown, the hook 1310 can be a straight rod. Figure 4b As shown, the hook 1310 can be formed by a plurality of straight rods that are sequentially deflected toward the central axis of the push cable 1100 to form a broken line rod structure. Figure 4c and Figure 4d As shown, the hook 1310 is a straight rod, one clamping arm 1320 extends to the left or right of the central axis of the push cable 1100, and the other clamping arm 1320 extends along the central axis of the push cable 1100. The shapes of the multiple hooks 1310 can be the same or different, as long as they form an annular closed structure.

[0076] See also Figure 3 、 Figure 5a and Figure 5b In this embodiment, the ends of the two hooks 1310 do not overlap; that is, the two hooks 1310 intersect and overlap to form a closed annular structure. This interlaced closed annular structure provides a more secure connection and locking force with the implant 200. Furthermore, when the two hooks 1310 are compressed by the push cable 1100, they can overlap, reducing the outer diameter of the clamp 1300. Therefore, the implant pushing device 10 of this embodiment has better passability in blood vessels and less damage to the patient.

[0077] like Figure 5a 、 Figure 5b and Figure 6 As shown, in order to limit the relative rotation between the clamping member 1300 and the push cable 1100, ensure that the clamping member 1300 is always staggered and overlapped in the same position and closed, and improve the stability of the annular closed structure, a limiter 1110 is provided at the distal end of the push cable 1100, and the limiter 1110 is provided with a limit hole 1111 along the axial direction of the push cable 1100. When the clamping member 1300 is in a free state, the hook 1310 and the distal end of the clamping arm 1320 both extend from the limit hole 1111. When the clamping member 1300 is in a locked state, the annular closed structure formed by the multiple hooks 1310 is located outside the limit hole 1111, that is, the hooks 1310 are located outside the limit hole 1111, and the distal ends of the clamping arms 1320 connected to the proximal ends of the hooks 1310 are closed together in the limit hole 1111. It can be understood that in other embodiments, when an annular closed structure is formed between the hook 1310 and the clamping arm 1320, the annular closed structure is located outside the limiting hole 1111, which means that the hook 1310 is located outside the limiting hole 1111, and the distal part of the clamping arm 1320 connected to or interlaced with the hook 1310 to form an annular closed structure is also located outside the limiting hole 1111, and the clamping arm 1320 connected to the proximal end of the hook 1310 is received in the limiting hole 1111 and is closed together with the proximal part of the other clamping arm 1320 in the limiting hole 1111.

[0078] The cross-section of the retaining hole 1111 is rectangular, oval, or oblate. In this embodiment, the two clamping arms 1320 of the clamping member 1300 extend through the retaining hole 1111 on the retaining member 1110. The cross-section of the retaining hole 1111 is oblate, which can accommodate the two hooks 1310 and the clamping arms 1320 in the locked state. The long axis dimension of the limiting hole 1111 is larger than the dimension of the outermost side of each clamping arm 1320 of the clamping member 1300 in the locked state on a plane perpendicular to the axial direction of the inner core 1200, and smaller than the dimension of each hook 1310 of the clamping member 1300 in the locked state on a plane perpendicular to the axial direction of the inner core 1200, ensuring that the clamping arm 1320 can be smoothly retracted into the limiting hole 1111 in the locked state, and the hook 1310 will press against the distal end of the limiting member 1110 and will not enter the limiting hole 1111; the short axis dimension of the limiting hole 1111 is roughly equal to the sum of the dimensions of the proximal ends of multiple clamping arms 1320 in a plane perpendicular to the axial direction of the inner core 1200, ensuring that the proximal ends of the clamping arms 1320 can be closed together in the limiting hole 1111, and the clamping arms 1320 can be smoothly extended out of the limiting hole 1111. The multiple clamping arms 1320 are tightly overlapped and do not deviate radially, thereby ensuring that the hooks 1310 connected to the clamping arms 1320 are tightly connected or staggered to form an annular closed structure, thereby ensuring the effectiveness of the connection.

[0079] The limiting member 1110 is preferably made of a relatively hard biocompatible material (eg, stainless steel) to ensure that the clamping member 1300 can overlap and close after being pressed by the limiting member 1110 .

[0080] The connection between the implant pushing device 10 and the implant 200 of this embodiment has a certain degree of flexibility for the following reasons: once the clamp 1300 is connected to the implant 200, the pushing assembly 1000 can deflect along the axial direction of the implant 200 within the plane where the connecting portion of the implant 200 lies, with a deflection angle C1 ranging from 0° to 180°. Furthermore, the pushing assembly 1000 can also deflect within a plane perpendicular to the plane where the connecting portion of the implant 200 lies, with a deflection angle C2 ranging from 0° to 180°. Therefore, the implant pushing device 10 of this embodiment has greater adaptability in curved blood vessels.

[0081] See also Figure 1 and Figure 8 The handle assembly 2000 is provided at the proximal end of the pushing device 1000 and is used to operate the connection or release between the pushing device 1000 and the implant 200. The handle assembly 2000 includes a handle 2100 and an axial drive control mechanism 2300 provided on the handle 2100.

[0082] The handle 2100 includes a first shell 2110 and a second shell arranged opposite to each other, which are fixedly connected together by buckles, adhesives, etc. The handle 2100 is used for the operator to hold, and the shape of its outer wall is not limited, as long as it is easy to hold.

[0083] The handle 2100 is fixedly connected to the proximal end of the push cable 1100, while the axial drive control mechanism is fixedly connected to the inner core 1200. The axial drive control mechanism 2300 is disposed at the proximal end of the handle 2100 and moves in a limited axial direction along the handle 2100. Thus, the operator can drive the inner core 1200 to move relative to the push cable 1100 by single-handedly operating the axial movement of the axial drive control mechanism 2300, thereby opening and locking the clamp 1300, thereby achieving the purpose of quickly releasing the implant 200.

[0084] Example 2

[0085] The structure of the implant pushing device of the second embodiment is substantially the same as that of the first embodiment, with the difference being that the shape of the clamping member in the second embodiment is different from that in the first embodiment.

[0086] Specifically, see Figures 9 to 11 Clamping arm 1320 is curved, facing away from the central axis. Hook 1310 is curved, with its opening pointing toward the central axis. The angle β between the tangent line of the arc of clamping arm 1320 and the central axis ranges from 90° to 150°. This curved shape of clamping arm 1320 and hook 1310 further reduces bending stress in clamping member 1300 and improves its fatigue strength.

[0087] Example 3

[0088] The structure of the implant pushing device of the third embodiment is substantially the same as that of the first embodiment, except that the clamping member structure in the third embodiment is different from that in the first embodiment.

[0089] like Figure 12As shown, each clamping arm 1320 comprises a first section 1320a and a second section 1320b connected from a proximal end to a distal end. The first section 1320a extends outward along the central axis, with an angle A between the first section 1320a and the central axis ranging from 120° ≤ A ≤ 180°. The second section 1320b is connected to the distal end of the first section 1320a and extends inward along the central axis. The angle B between the second section 1320b and the first section 1320a ranges from 90° ≤ B ≤ 150°. Thus, when the clamping member 1300 of this embodiment is in a free state, the two clamping arms 1320 intersect. The distal end of the second section 1320b of the clamping arm 1320 has a hook 1310. The hook 1310 can be one or two short rods, arc-shaped rods, or a combination of short and arc-shaped rods, extending toward or away from the central axis of the push cable 1100. In this embodiment, the ends of the hooks 1310 at the distal ends of the two clamping arms 1320 are arranged relative to each other toward the central axis. When the clamping arms 1320 are retracted toward the proximal end and the clamping member 1300 is in a locked state, the ends of the hooks 1310 are staggered and overlapped to form a closed loop structure.

[0090] like Figure 13 As shown, when the clamping member 1300 is in a free state, the first section 1320a of the clamping arm 1320 is accommodated in the pushing steel cable 1100 and the limiting member 1110, and the second section 1320b of the clamping arm 1320 extends from the limiting hole 1111 of the limiting member 1110 and expands radially.

[0091] like Figure 14 As shown, when the push cable 1100 and the inner core 1200 move relative to each other, the second section 1320b of the clamping arm 1320 is squeezed by the limiting hole 1111 of the limiting member 1110 until the clamping arm 1320 is completely retracted into the limiting member 1110. The hook 1310 overlaps and intersects with the outside of the limiting member 1110, forming a ring-shaped closed structure, locking the connection with the implant 200. During the locking process, the entire clamping member 1300 overlaps and intersects twice, making the locking more secure and effectively preventing failure of the connection between the implant pushing device 10 and the implant 200.

[0092] Example 4

[0093] The structure of the implant pushing device of the fourth embodiment is substantially the same as that of the implant pushing device of the first embodiment, except that the structure of the handle assembly of the fourth embodiment is different from that of the handle assembly of the first embodiment.

[0094] Specifically, see Figures 15 to 17The handle 2100 includes a first outer shell 2110 and a second outer shell 2120. A control groove 2200 is axially defined on the handle 2100. The length of the control groove 2200 is greater than or equal to the maximum relative motion distance between the push cable 1100 and the inner core 1200, thereby enabling the clamping member 1300 to transition between a free state and a locked state. The control groove 2200 can be directly defined in the first outer shell 2110 or the second outer shell 2120, or a groove can be defined in each of the first and second outer shells 2110, 2120, and then snapped together to form the control groove 2200.

[0095] The axial drive control mechanism 2300 includes a sliding member 2330 connected to the push steel cable 1100 or the inner core 1200, and a connecting member 2320 connected to the sliding member 2330. The connecting member 2320 passes through the control groove 2200 to the outside of the handle 2100. The connecting member 2320 slides axially and drives the sliding member 2330 to move, thereby driving the axial relative movement between the push steel cable 1100 and the inner core 1200.

[0096] In this embodiment, the slider 2330 is connected to the proximal end of the push cable 1100 via threaded, clipped, interference fit, pinned, welded, or riveted connections commonly used in the art. The proximal end of the inner core 1200 extends from the proximal end of the push cable 1100 and is secured to the handle 2100 via an inner core fixture. The inner core fixture includes a travel portion 1230 fixedly connected to the inner core 1200 and an adjustment portion 2130 fixedly connected to the handle 2100. The adjustment portion 2130 is movably connected to the travel portion 1230. In this embodiment, a screw is connected to the proximal end of the inner core 1200, serving as the travel portion 1230. A nut is provided in the handle 2100 as the adjustment portion 2130, with the screw and nut being compatible. Therefore, when assembling the inner core 1200 in the handle 2100, the operator can adjust the relative position between the inner core 1200, the handle 2100 and the push cable 1100 by adjusting the position of the nut on the screw, so as to prevent the inner core 1200 from being excessively pulled or being too loose, thereby affecting the locking effect of the clamp 1300.

[0097] A guide member is provided within the handle 2100 to restrict the sliding member 2330 to axial movement along the guide member, ensuring smooth sliding of the sliding member 2330. The guide member may be in the form of a groove in which the sliding member 2330 slidably fits, or in the form of a rod on which the sliding member 2330 is mounted and moves axially along the rod.

[0098] The connecting member 2320 is installed in the control groove 2200 and passes through the control groove 2200 to the outside of the handle 2100, which is convenient for the operator to operate.

[0099] The proximal or distal end of the slider 2330 is connected to an elastic member 2500. The compression or reset of the elastic member 2500 drives the axial movement of the axial drive control mechanism 2300, thereby driving the axial relative movement between the push cable 1100 and the inner core 1200. Specifically, when the slider 2330 is connected to the inner core 1200, the elastic member 2500 is connected to the distal end of the slider 2330; when the slider 2330 is connected to the push cable 1100, the elastic member 2500 is connected to the proximal end of the slider 2330. Therefore, when the elastic member 2500 is compressed, the pushing cable 1100 moves toward the proximal end, and the clamping member 1300 extends from the pushing cable 1100 and is in a free state, and can be connected to the implant 200; when the elastic member 2500 is reset due to its own elasticity, the pushing cable 1100 moves toward the distal end, and the clamping member 1300 retracts into the pushing cable 1100, and the hooks 1310 overlap and interlace to form an annular closed structure, locking the connection with the implant 200.

[0100] In this embodiment, the elastic member 2500 is in the form of a spring. It is understandable that in other embodiments, the elastic member 2500 may also be in other forms such as an elastic rod.

[0101] A drive stopper is also provided axially within the handle 2100 to limit the radial movement of the elastic member 2500. This stopper can be positioned proximally or distally on the guide member 2180. Specifically, in this embodiment, a strip-shaped groove is provided within the handle 2100 to serve as the drive stopper, and the elastic member 2500 is accommodated within the strip-shaped groove. It is understood that in other embodiments, the elastic member 2500 can also be mounted on a rod-shaped body, with the rod-shaped body serving as the drive stopper.

[0102] In this embodiment, due to the elastic force of the elastic member 2500, the axial drive control mechanism 2300 is squeezed by the elastic member 2500, and the clamping member 1300 remains locked, thereby preventing accidental disconnection between the push assembly 1000 and the implant 200. Only when the operator operates the axial drive control mechanism 2300 to overcome the elastic force of the elastic member 2500, the elastic member 2500 is compressed, the push cable 1100 is withdrawn, and the clamping member 1300 extends from the push cable 1100, releasing the connection with the implant 200. This operation is simple and convenient.

[0103] Example 5

[0104] The structure of the implant pushing device of the fifth embodiment is substantially the same as that of the implant pushing device of the fourth embodiment, except that the structure of the handle assembly of the fifth embodiment is different from that of the handle assembly of the fourth embodiment.

[0105] See also Figure 18 and Figure 19The handle 2100 is axially provided with a control slot 2200, a first latching position 2210 at the distal end, and a second latching position 2220 at the proximal end. The first latching position 2210 and the second latching position 2220 are both radially offset relative to the control slot 2200. The first latching position 2210 and the second latching position 2220 can be radially offset on the same side of the control slot 2200, or radially offset on either side of the control slot 2200. The first latching position 2210 and the second latching position 2220 are both connected to the control slot 2200, thereby allowing the axial drive control mechanism 2300 to move within the control slot 2200 and the first latching position 2210 and the second latching position 2220. When the axial drive control mechanism 2300 switches between the first latching position 2210 and the second latching position 2220, the clamping member 1300 switches between a locked state and a free state. Specifically, when the sliding member 2330 of the axial drive control mechanism 2300 is connected to the pushing steel cable 1100, and the connecting member 2320 of the axial drive control mechanism 2300 is switched to the second clamping position 2220 at the proximal end, the pushing steel cable 1100 moves proximally, and the clamping member 1300 extends from the pushing steel cable 1100 and is in a free state, and can be connected to the implant 200; when the connecting member 2320 is switched to the first clamping position 2210 at the distal end, the pushing steel cable 1100 moves distally, the clamping member 1300 retracts into the pushing steel cable 1100, and the hooks 1310 are staggered and overlapped to form an annular closed structure, and the clamping member 1300 is converted to a locked state, locking the connection with the implant 200. It can be understood that in other embodiments, the sliding member 2330 can also be connected to the inner core 1200. When the axial drive control mechanism 2300 is located in the first locking position 2210, the clamping member 1300 is in a free state; when the axial drive control mechanism 2300 is located in the second locking position 2220, the clamping member 1300 is in a locked state.

[0106] In this embodiment, when switching the position of the axial drive control mechanism 2300, the connecting member 2320 slides axially along the control groove 2200 until it reaches the first locking position 2210 or the second locking position 2220, and then shifts toward the first locking position 2210 or the second locking position 2220, so that the axial drive control mechanism 2300 can be locked into the first locking position 2210 or the second locking position 2220, completing the conversion of the clamping member 1300, and then locking or releasing the connection with the implant 200. The operation is simple and the implant 200 can be quickly released.

[0107] Example 6

[0108] See also Figure 20 The implant delivery system 100 provided in the sixth embodiment includes an implant pushing device 10, an expansion device 20, a loading device 30, a hemostatic device 40, and an outer sheath 50. The structure of the implant pushing device 10 is substantially the same as that of the aforementioned implant pushing device 10, and will not be described in detail herein.

[0109] See also Figure 21 The distal end of the expansion device 20 passes through the distal end of the outer sheath 50 to form an expansion assembly. The distal end of the expansion assembly follows the track established by the guide wire (not shown in the figure) to reach the predetermined treatment site in the patient's body, and then the expansion device 20 is withdrawn, leaving the outer sheath 50 in the body, thus establishing a passage from the outside to the inside. Figure 22 After establishing the passage from the outside to the inside of the body, the proximal end of the loading device 30 is first connected to the distal end of the hemostatic device 40. Then, the distal end of the implant pushing device 10 is passed through the hemostatic device 40 and the loading device 30 in sequence, and then detachably connected to the connecting portion of the proximal end of the implant 200. The pushing device 10 is then withdrawn proximally to store the implant 200 in the loading device 30. Figure 23 The distal end of the loading device 30 is connected to the proximal end of the outer sheath 50, and the pushing device 10 is operated to push the implant 200 toward the distal end until the implant 200 is pushed out of the distal end of the outer sheath 50. The implant 200 is released from the connection with the implant pushing device 10 and returns to the expanded state, completing the release and implantation of the implant 200.

[0110] See also Figure 24 The outer sheath 50 is hollow inside to allow the expansion device 20 or the push cable 1100 to pass through. The wall of the outer sheath 50 is a multi-layer structure, which includes a polytetrafluoroethylene layer, a stainless steel braided layer and a polyether block amide layer from the inside to the outside. The polytetrafluoroethylene layer is located in the innermost layer. Due to its extremely low friction coefficient, the push cable 1100 and the implant 200 have little resistance when passing through the outer sheath 50; the polytetrafluoroethylene layer is acid and alkali resistant, and blood, developing liquid, etc. will not damage the polytetrafluoroethylene layer; the stainless steel braided layer has high strength, so the outer sheath 50 is not easily damaged. The polyether block amide layer is located in the outermost layer. The polyether block amide layer has good mechanical elastic properties, chemical stability and thermal stability, which makes the outer sheath 50 have good bending properties and is not easy to damage. The outer sheath 50 also includes at least one side branch for connecting to an external device (not shown) to inject liquids such as drugs or contrast agents, and can also prevent air from entering the blood vessels during surgery. A sheath seat 52 is provided at the proximal end of the outer sheath 50 to connect with the expansion device 20 or the loading device 30. The sheath seat 52 is T-shaped or Y-shaped, and is T-shaped here.

[0111] See also Figure 25 An elastic seal 521 is provided in the sheath seat 52. The elastic seal 521 is made of an elastic material, and the elastic seal 521 is provided with at least one aperture along the axial direction of the pushing device 10 for the passage of the pushing cable 1100.

[0112] See also Figure 26 、 Figure 27a and Figure 27bThe elastic seal 521 is cylindrical, with a first elongated slit 5211 formed at the proximal end of the elastic seal 521 and a second elongated slit 5212 formed at the distal end. The sum of the thicknesses of the first slit 5211 and the second slit 5212 equals the thickness of the elastic seal 521, where the thickness refers to the axial length of the sheath holder 52. In this embodiment, the thickness of the first slit 5211 and the second slit 5212 are the same, both equal to half the thickness of the elastic seal 521. That is, the first slit 5211 is located at the proximal half of the elastic seal 521, and the second slit 5212 is located at the distal half of the elastic seal 521. There is no overlap between the first slit 5211 and the second slit 5212 in the thickness direction. The first slit 5211 and the second slit 5212 are oriented in different directions. In this embodiment, the first slit 5211 extends in the horizontal direction, while the second slit 5212 extends in the longitudinal direction. The projections of the first slit 5211 and the second slit 5212 on the distal surface of the elastic seal 521 intersect. In this embodiment, the intersection is the center of the surface of the distal end of the elastic seal 521. Preferably, the projections of the first slit 5211 and the second slit 5212 on the distal surface of the elastic seal 521 are perpendicular to each other, that is, the two form a cross. Because the two slits on the proximal and distal surfaces of the elastic seal 521 intersect, the intersection is relatively fragile and easier to penetrate. This intersection becomes the only channel for the interventional tube body such as the push wire cable 1100 or the expansion device 20 to pass through the elastic seal 521. Because the elastic seal 521 is made of elastic material, when the interventional tube body is withdrawn, the pierced elastic seal 521 tends to close again, and after closing, there are basically no holes or gaps. Therefore, the elastic seal 521 of this embodiment can achieve a self-sealing effect. The elastic seal 521 of this embodiment is installed in the sheath tube seat 52. After the push cable 1100 is passed through and pulled out of the elastic seal 521 three times in a row, after testing, the sealing performance of the sheath tube seat 52 can still reach 1.5ATM (standard atmospheric pressure), which can effectively prevent blood leakage and ensure air tightness.

[0113] See also Figure 28 The expansion device 20 includes an expansion tube 21 and an expansion tube seat 22. The proximal end of the expansion tube 21 is connected to the distal end of the expansion tube seat 22. The expansion tube 21 is made of polyethylene, and the outer diameter of the expansion tube 21 is slightly smaller than the inner diameter of the outer sheath 50. The expansion tube 21 also includes a pointed tip 23 at the distal end. The pointed tip 23 is tapered, and the outer diameter gradually increases from the distal end to the proximal end. Therefore, when the expansion assembly composed of the expansion device 20 and the outer sheath 50 advances along the guide wire and passes through a narrow blood vessel, the pointed tip 23 can expand the blood vessel, facilitating the smooth passage of the expansion assembly.

[0114] See also Figure 29After establishing the passage from the outside to the inside of the body, the distal end of the loading device 30 is connected to the proximal end of the outer sheath 50 by means of a threaded connection or the like. The hollow loading device 30 is used to accommodate and pass the compressed implant 200 .

[0115] See also Figure 30 The hemostatic device 40 is connected to the proximal end of the loading device 30. The hemostatic device 40 is hollow and communicates with the loading device 30. The push cable 1100 passes through the proximal end of the hemostatic device 40 and exits from the distal end of the hemostatic device 40 to connect with the implant 200. The hemostatic device 40 is provided with an elastic seal 41. The structure of the elastic seal 41 can be a common sealing ring, a sealing gasket, or the same as the structure of the elastic seal 521 in the sheath seat 52. It is understood that in other embodiments, the loading device 30 can also be provided with an elastic seal. In this case, the implant delivery system 100 may not require the hemostatic device 40. The structure of the elastic seal in the loading device 30 can be a sealing ring or a sealing gasket, or the same as the structure of the elastic seal 521 in the sheath seat 52.

[0116] It is understood that, in other embodiments, the implant delivery system 100 may not include the loading device 30 , and the proximal end of the outer sheath 50 may be directly connected to the distal end of the hemostatic device 40 .

[0117] It should be noted that the various embodiments in this specification are described in a progressive manner, and each embodiment focuses on the differences from other embodiments. The same and similar parts between the various embodiments can be referenced to each other.

[0118] The above disclosure is merely a preferred embodiment of the present invention and certainly cannot be used to limit the scope of the present invention. Therefore, equivalent changes made according to the claims of the present invention are still within the scope of the present invention.

Claims

1. A lockable implant pushing device, comprising a pushing assembly and a handle assembly connected to the proximal end of the pushing assembly, characterized in that: The pushing assembly includes a hollow pushing steel cable, an inner core movably inserted into the pushing steel cable, and a clamping member provided at the distal end of the inner core and detachably connected to the implant; the clamping member includes at least two clamping arms, at least one of which is provided with a hook at the distal end, the hook extending toward or away from the central axis of the pushing steel cable, and the extension directions of the plurality of hooks are different; The planes where the ends of at least two of the hooks lie do not overlap; The clamping member has a free state and a locked state. When the clamping member is in the free state, the distal end of the clamping arm extends out of the distal end of the push steel cable, and all the distal ends of the clamping arms radiate radially in different directions; when the clamping member is in the locked state, all the clamping arms retract into the push steel cable and converge towards the central axis of the push steel cable, and the ends of at least two of the hooks are staggered to form an annular closed structure, and the ends of the hooks do not touch but the radial projections on the same plane overlap.

2. The implant pushing device according to claim 1, characterized in that In the free state, the angle between at least one of the clamping arms and the central axis of the push steel cable ranges from 90° to 150° or from 200° to 270°, and the angles between the two clamping arms forming an annular closed structure and the central axis of the push steel cable are not equal.

3. The implant pushing device according to claim 1, characterized in that A limiting piece is provided at the distal end of the pushing steel cable, and a limiting hole is provided on the limiting piece along the axial direction of the pushing steel cable. When the clamping piece is in a free state, the hook piece and the distal end of the clamping arm both extend from the limiting hole. When the clamping piece is in a locked state, the hook piece is located outside the limiting hole, and the distal end of the clamping arm connected to the proximal end of the hook piece is closed together in the limiting hole.

4. The implant pushing device according to claim 3, characterized in that The major axis dimension of the limiting hole is larger than the dimension of the outermost side of each clamping arm of the clamping member in a locked state on a plane perpendicular to the axial direction of the inner core, and smaller than the dimension of each hook of the clamping member in a locked state on a plane perpendicular to the axial direction of the inner core; the minor axis dimension of the limiting hole is roughly equal to the sum of the dimensions of the proximal ends of multiple clamping arms on a plane perpendicular to the axial direction of the inner core.

5. The implant pushing device according to claim 1, characterized in that: The handle assembly includes a handle and an axial drive control mechanism disposed on the handle. The axial drive control mechanism moves axially relative to the handle to drive the axial relative movement between the push cable and the inner core.

6. The implant pushing device according to claim 5, characterized in that: The handle is provided with a control groove along the axial direction, and the axial drive control mechanism moves axially in the control groove.

7. The implant pushing device according to claim 6, characterized in that: The handle assembly also includes an elastic member arranged at the proximal end or distal end of the axial drive control mechanism. The compression or reset of the elastic member drives the axial movement of the axial drive control mechanism to drive the axial relative movement between the push cable and the inner core.

8. The implant pushing device according to claim 7, characterized in that: The distal end of the axial drive control mechanism is connected to the pushing steel cable, and the proximal end of the axial drive control mechanism is connected to the elastic member.

9. The implant pushing device according to claim 6, characterized in that: The handle is further provided with at least two latching positions, which are radially offset relative to the control groove and communicate with the control groove, and the axial drive control mechanism moves in the control groove and the latching positions.

10. The implant pushing device according to claim 9, characterized in that: The locking positions include a first locking position at the distal end and a second locking position at the proximal end. When the axial drive control mechanism switches between the first locking position and the second locking position, the clamping member switches between a locked state and a free state.

11. The implant pushing device according to claim 10, characterized in that: The axial drive control mechanism is connected to the push cable. When the axial drive control mechanism is in the first clamping position, the clamping member is in a locked state; when the axial drive control mechanism is in the second clamping position, the clamping member is in a free state.

12. An implant delivery system, characterized in that: The implant pushing device comprises the implant pushing device according to any one of claims 1 to 11, further comprising an outer sheath having a certain axial length, wherein the implant pushing device is movably mounted in the outer sheath and is detachably connected to the proximal end of the outer sheath.

13. The implant delivery system according to claim 12, wherein: The implant delivery system further comprises an expansion device, which is movably installed in the outer sheath tube, and the proximal end of the expansion device is detachably connected to the proximal end of the outer sheath tube.

14. The implant delivery system according to claim 13, wherein: The implant delivery system further comprises a loading device, which is detachably connected between the proximal end of the outer sheath and the distal end of the pushing device.

15. The implant delivery system according to claim 14, wherein: The implant delivery system further includes a hemostatic device detachably connected between the loading device and a distal end of the pushing device.

16. The implant delivery system according to claim 15, wherein: At least one of the outer sheath, the loading device and the hemostasis device is provided with an elastic sealing member, and the elastic sealing member is provided with at least one aperture along the axial direction of the pushing device.

17. The implant delivery system according to claim 16, wherein: A first slit is formed at the proximal end of the elastic seal, and a second slit is formed at the distal end of the elastic seal. The sum of the thicknesses of the first slit and the second slit is equal to the thickness of the elastic seal. The directions of the first slit and the second slit are different. The projection of the first slit on the distal surface of the elastic seal intersects with the projection of the second slit on the distal surface of the elastic seal.

18. The implant delivery system of claim 17, wherein: The projection of the first slit on the distal end surface of the elastic seal is perpendicular to the projection of the second slit on the distal end surface of the elastic seal.

Images