Transapical implantation system for a heart assist booster pump

Abstract

The application discloses a trans-apical implantation system of a heart auxiliary pressurizing pump and relates to the technical field of medical devices, which can solve the problem that the existing heart auxiliary pressurizing pump implantation needs to cut open the heart wall, the surgical process is troublesome, and the risk is high, and can effectively reduce the implantation difficulty of the pump body assembly compared with the prior art. The trans-apical implantation system of the heart auxiliary pressurizing pump comprises an outer tube, an inner push tube, a pump body assembly, the pump body assembly comprises a pump body main body and a reversible paddle structure, and a plurality of locking hooks are movably connected to the outer peripheral wall of the pump body main body in the circumferential direction; the end, away from the pump body main body, of the locking hook is provided with a bent embedding section, and the bent embedding sections of the plurality of locking hooks are all bent in the clockwise direction or the counterclockwise direction; the outer peripheral wall of the pump body main body is further provided with a first rotation limiting structure, the end of the inner push tube is provided with a second rotation limiting structure, and the pump body assembly and the inner push tube are synchronously rotated through the mutually matched first rotation limiting structure and the second rotation limiting structure.

Description

Technical Field

[0001] This invention relates to the field of medical device technology, specifically to a transapical implantable system for a cardiac assist pump. Background Technology

[0002] When the heart is in a diseased state and its pumping capacity is insufficient, resulting in insufficient blood output to meet the body's needs, it is often necessary to implant a cardiac assist pump in the ventricle. This pump assists in pressurizing the heart as it pumps blood into the arteries, ensuring that the heart can pump out sufficient volume and pressure of blood.

[0003] A cardiac assist pump typically needs to be implanted in the left ventricle. Current implantation methods require incising the aorta and vein, stopping the heart from beating, then incising the heart wall before suturing the cardiac assist pump into the left ventricle, ensuring the pump blades face the aorta, and finally suturing the heart wall, arteries, veins, and other tissues.

[0004] The entire surgical implantation process of the cardiac assist pump is quite complicated, requires a high level of surgical experience from the surgeon, and carries significant risks, thus urgently requiring improvement.

[0005] Based on the above background, the inventors designed a transapical implantable system for a cardiac assist pump to solve at least one of the above problems, and hereby file this application. Summary of the Invention

[0006] The purpose of this application is to provide a transapical implantation system for a cardiac assist pump, which can solve the problems of existing cardiac assist pumps requiring incision of the heart wall, resulting in complicated surgical procedures and high surgical risks.

[0007] To address the above problems, this application provides the following technical solution:

[0008] This application provides a transapical implantable system for a cardiac assist pump, comprising: an outer tube for establishing an implantation channel, an inner push tube disposed within and slidably connected to the outer tube, and a pump assembly mounted at the end of the inner push tube, wherein:

[0009] The pump body assembly includes a pump body body and a plurality of locking hooks connected to the outer peripheral wall of the pump body body along the circumferential direction of the pump body body.

[0010] The axial direction of the connecting shaft of the locking hook is parallel to the tangential direction of the outer periphery of the pump body;

[0011] The locking hook has a bent embedding section at one end away from the pump body for embedding into heart tissue. The bent embedding sections of multiple locking hooks are all bent or folded in a clockwise or counterclockwise direction along the circumference of the pump body.

[0012] The outer peripheral wall of the pump body is also provided with a first rotation limiting structure, and the end of the inner push tube is provided with a second rotation limiting structure. The pump body assembly and the inner push tube rotate synchronously with each other through the mutually adapted first and second rotation limiting structures.

[0013] The bent and embedded section of the locking hook is also provided with several barbed structures or abutting structures.

[0014] Optionally, the pump body assembly further includes a blade mounting base disposed on the output end of the pump body body, and a blade structure mounted on the blade mounting base.

[0015] Optionally, the pump body assembly further includes a blade mounting base disposed on the output end of the pump body body;

[0016] The top of the blade mounting base is provided with multiple movable connection slots for mounting the blade structure.

[0017] The blade structure includes a fixedly connected blade body and a blade seat, with the blade body movably connected to a movable connecting groove via the blade seat.

[0018] Optionally, it also includes a locking assembly for locking the flipped blade structure, the locking assembly being located at the bottom of the blade seat;

[0019] The side of the movable connecting groove is also provided with a locking triangular groove for cooperating with the locking assembly;

[0020] The locking assembly includes a top-pressure spring and a T-shaped locking rod movably connected to the bottom of the blade seat. One end of the top-pressure spring presses against the T-shaped locking rod, and the other end presses against the inside of the blade seat.

[0021] Optionally, the first rotation limiting structure is a rotation limiting groove, the bottom of which extends to the bottom of the pump body.

[0022] The second rotation limiting structure is a rotation limiting protrusion located at the end of the inner push tube, and the width of the rotation limiting protrusion is the same as the width of the rotation limiting groove.

[0023] Optionally, the inner push tube includes a main body, and a gripping part and a mounting part located at both ends of the main body;

[0024] The total length of the inner tube is greater than the length of the outer tube;

[0025] The mounting part is provided with a placement plate at one end near the main body, and the placement plate is also provided with wire passage holes;

[0026] A baffle extends upward from the top of the mounting part, and the first rotation limiting structure is disposed on the baffle and extends to the bottom of the mounting part.

[0027] Optionally, the outer peripheral wall of the grip is spirally connected to a detachable knob sleeve;

[0028] Both the gripping part and the main body are hollow circular tubes.

[0029] Optionally, the end of the outer tube that extends into the left ventricle is also provided with a hook release slit;

[0030] The shape and number of the hook release slots are adapted to the shape and number of the locking hooks;

[0031] A spring is fitted on the connecting shaft of the locking hook, with one end of the spring located on the pump body and the other end located on the locking hook.

[0032] Optionally, the outer tube includes a section that restricts rotation and a section that allows free rotation;

[0033] The outer tube's rotation-restricting section is provided with strip-shaped protrusions arranged parallel to its axial direction;

[0034] The outer peripheral wall of the inner push tube is fixed with a notch structure that matches the strip-shaped protrusion;

[0035] With the inner push tube's notch structure fastened to the strip-shaped protrusion, the relative rotation between the inner push tube and the outer tube is restricted.

[0036] With the concave structure of the inner push tube detached from the strip protrusion, the inner push tube and the outer tube can rotate freely relative to each other.

[0037] Optionally, the end of the outer tube that extends into the left ventricle is further provided with a limiting protrusion for restricting the extension length of the inner tube.

[0038] The beneficial effects of this invention are:

[0039] This application employs an outer tube, an inner push tube, and a pump assembly. The pump assembly features a flip-up impeller structure, and the pump body has a locking hook on its outer periphery. Furthermore, this application incorporates a first rotation-limiting structure and a second rotation-limiting structure, allowing the inner push tube and pump assembly to rotate synchronously. During use, after establishing an implantation channel using the outer tube, the inner push tube pushes the pump assembly from the implantation channel into the left ventricle. Once the desired position is reached, the surgeon rotates the inner push tube, causing the pump body to rotate. This allows the bent, embedded section of the locking hook on the pump body to embed and fix into the heart wall tissue, completing the implantation of the pump assembly. The outer tube and inner push tube are then removed, and the wound is sutured. Compared to existing technologies, this application eliminates the need to cut arteries, veins, and the heart wall during pump assembly implantation, effectively reducing the difficulty of implantation. Attached Figure Description

[0040] Figure 1 This is a schematic diagram of the structure of an embodiment of this application before use.

[0041] Figure 2 for Figure 1 A schematic diagram of the cross-sectional structure of AA.

[0042] Figure 3 This is a schematic diagram of the pump body assembly in an embodiment of this application.

[0043] Figure 4 for Figure 3 A magnified view of a portion of point A in the middle.

[0044] Figure 5 This is a cross-sectional view of the push tube in an embodiment of this application.

[0045] Figure 6 This is a schematic diagram of the pump assembly implanted via the apex of the heart in an embodiment of this application.

[0046] Figure 7 This is a schematic diagram of the pump body assembly after implantation in an embodiment of this application.

[0047] Explanation of reference numerals in the attached drawings: 1-Outer tube, 11-Hook release slot, 12-Limiting protrusion, 13-Strip protrusion, 2-Inner push tube, 21-Main body, 22-Mounting part, 221-Placement plate, 222-Baffle, 223-Rotation limiting protrusion, 224-Wire passage hole, 23-Grip part, 24-Notch structure, 3-Pump body assembly, 31-Pump body main body, 311-Rotation limiting groove, 32-Locking hook, 321-Bent embedding section, 322-Barbed structure, 33-Impeller mounting seat, 331-Movable connecting groove, 332-Locking triangular groove, 34-Impeller structure, 341-Impeller body, 342-Impeller seat, 35-Locking assembly, 351-Top pressure spring, 352-Clamping rod, 36-Guide wire hole ring, 41-Left ventricle. Detailed Implementation

[0048] The present invention will be further described in detail below with reference to the embodiments and accompanying drawings, but the embodiments of the present invention are not limited thereto.

[0049] In the description of this invention, it should be noted that the terms "center," "upper," "lower," "left," "right," "vertical," "longitudinal," "lateral," "horizontal," "inner," "outer," "front," "rear," "top," and "bottom," etc., indicate the orientation or positional relationship based on the orientation or positional relationship shown in the accompanying drawings, or the orientation or positional relationship commonly used when the product of this invention is in use. They are only for the convenience of describing this invention and simplifying the description, and do not indicate or imply that the device or element referred to must have a specific orientation, or be constructed and operated in a specific orientation. Therefore, they should not be construed as limitations on this invention.

[0050] In the description of this invention, it should also be noted that, unless otherwise explicitly specified and limited, the terms "set up," "have," "install," "connect," and "connect" should be interpreted broadly. For example, they can refer to a fixed connection, a detachable connection, or an integral connection; they can refer to a mechanical connection or an electrical connection; they can refer to a direct connection or an indirect connection through an intermediate medium; and they can refer to the internal communication between two components. Those skilled in the art can understand the specific meaning of the above terms in this invention based on the specific circumstances.

[0051] The present invention will now be described in detail with reference to the accompanying drawings and embodiments.

[0052] like Figures 1 to 7 As shown, this embodiment provides a transapical implantation system for a cardiac assist pump, comprising: an outer tube 1 for establishing an implantation channel, an inner push tube 2 disposed within and slidably connected to the outer tube 1, and a pump assembly 3 installed at the end of the inner push tube 2, wherein:

[0053] The pump body assembly 3 includes a pump body body 31 and a flip-type blade structure 34 provided on the output end of the pump body body 31, as well as a plurality of locking hooks 32 that are flipped and connected to the outer peripheral wall of the pump body body 31 along the circumference of the pump body body 31. The locking hooks 32 can also be rigidly connected or folded to the pump body body 31.

[0054] The axial direction of the connecting shaft of the locking hook 32 is parallel to the tangential direction of the outer periphery of the pump body 31;

[0055] The locking hook 32 is provided with a bent embedding section 321 for embedding into heart tissue at one end away from the pump body 31. The bent embedding sections 321 of the multiple locking hooks 32 are all bent or bent in a clockwise or / and counterclockwise direction along the circumference of the pump body 31. Specifically, the bent embedding section 321 in this embodiment can be L-shaped or arc-shaped.

[0056] The outer peripheral wall of the pump body 31 is also provided with a first rotation limiting structure, and the end of the inner push tube 2 is provided with a second rotation limiting structure. The pump body assembly 3 and the inner push tube 2 rotate synchronously through the mutually adapted first and second rotation limiting structures.

[0057] In this embodiment, the pump body assembly 3 further includes a blade mounting base 33 disposed on the output end of the pump body 31, and a blade structure 34 mounted on the blade mounting base 33.

[0058] The blade structure 34 is flipped and connected to the blade mounting base 33. Alternatively, the blade structure 34 can be rigidly connected to the blade mounting base 33 or folded and connected to the blade mounting base 33. Both rigid and folded connections of the blade structure 34 to the blade mounting base 33 are relatively conventional techniques and will not be elaborated here.

[0059] This embodiment uses an outer tube 1, an inner push tube 2, and a pump assembly 3. The impeller structure 34 of the pump assembly 3 is a flip-up impeller structure 34. A locking hook 32 is provided on the outer periphery of the pump body 31 of the pump assembly 3. At the same time, this embodiment also provides a first rotation limiting structure and a second rotation limiting structure, so that the inner push tube 2 and the pump assembly 3 can rotate synchronously. In this embodiment, after establishing an implantation channel using the outer tube 1, the inner push tube 2 can push the pump assembly 3 from inside the implantation channel into the left ventricle 41. After reaching the ideal position, the surgeon twists the inner push tube 2 to rotate, thereby driving the pump body 31 of the pump assembly 3 to rotate, so that the bent embedding section 321 of the locking hook 32 on the pump body 31 can be embedded and fixed into the heart wall tissue, completing the implantation of the pump assembly 3. Then, the outer tube 1 and the inner push tube 2 are removed, and the wound is sutured. Compared with the prior art, the implantation of the pump body component 3 in this embodiment does not require cutting open the arteries, veins and heart wall, which can effectively reduce the difficulty of implanting the pump body component 3.

[0060] In this embodiment, the blade structure 34 is a flip-type blade structure 34. In some embodiments, technicians may also use a fixed conventional blade structure 34, which will not be described in detail here.

[0061] In this embodiment, the top of the blade mounting base 33 is provided with a plurality of movable connecting slots 331 for mounting the blade structure 34;

[0062] The paddle structure 34 includes a fixedly connected paddle body 341 and paddle seat 342. The paddle body 341 is flipped and connected to the movable connecting groove 331 through the paddle seat 342. This means that before the pump assembly 3 is pushed out of the implantation channel of the outer tube 1, the multiple paddle structures 34 occupy a small volume and are in a retracted state. After the pump assembly 3 is pushed out of the implantation channel of the outer tube 1, when the pump body 31 is started to drive the paddle body 341 to rotate, the paddle structure 34 will automatically unfold under the action of centrifugal force. The movable connecting groove 331 is set on the top of the paddle mounting seat 33, so that the paddle structure 34 will not be unstable when rotating to assist in blood pressurization.

[0063] In this embodiment, a locking component 35 is also included for locking the flipped blade structure 34. The locking component 35 is disposed at the bottom of the blade seat 342.

[0064] The side of the movable connecting groove 331 is also provided with a locking triangular groove 332 for cooperating with the locking assembly 35;

[0065] The locking assembly 35 includes a top pressure spring 351 and a T-shaped locking rod 352 movably connected to the bottom of the blade seat 342. One end of the top pressure spring 351 presses against the T-shaped locking rod 352, and the other end presses against the blade seat 342.

[0066] By setting a locking component 35 and a locking triangular groove 332 on the side of the movable connecting groove 331, the T-shaped locking rod 352 of the locking component 35 can slide into and lock into the locking triangular groove 332 after the blade structure 34 is first unfolded, thereby completing the further locking of the blade structure 34 and improving the stability of the blade structure 34 during rotation.

[0067] In this embodiment, the bent embedding section 321 of the locking hook 32 is also provided with a number of barbed structures 322 to improve the stability of the bent embedding section 321 after it is implanted into the heart wall tissue and prevent the pump body 31 from falling off.

[0068] In this embodiment, the first rotation limiting structure is a rotation limiting groove 311, and the bottom of the rotation limiting groove 311 extends to the bottom of the pump body 31.

[0069] The second rotation limiting structure is a rotation limiting protrusion 223 located at the end of the inner push tube 2. The width of the rotation limiting protrusion 223 is the same as the width of the rotation limiting groove 311.

[0070] The specific construction of the first and second rotation limiting structures in this embodiment can also be interchanged, and technicians can set them according to their needs, which will not be elaborated here. By setting the first and second rotation limiting structures, the rotation of the inner push tube 2 can drive the rotation of the pump body 31, thereby allowing the bent embedding section 321 of the locking hook 32 to be implanted into the heart wall tissue.

[0071] In this embodiment, the inner push tube 2 includes a main body 21, and a gripping part 23 and a mounting part 22 located at both ends of the main body 21;

[0072] The total length of the inner push tube 2 is greater than the length of the outer tube 1, ensuring that the inner push tube 2 can push the pump body assembly 3 out of the outer tube 1;

[0073] The mounting part 22 is provided with a placement plate 221 at one end near the main body part 21. The placement plate 221 is also provided with a wire hole 224 to facilitate the wires of the pump body assembly 3 to be led out from the inner push tube 2 to the outside of the heart.

[0074] A baffle 222 extends upward from the top of the mounting part 22. The first rotation limiting structure is provided on the baffle 222 and extends to the bottom of the mounting part 22. By setting the baffle 222, the stability of the pump body assembly 3 after it is installed in the mounting part 22 of the inner push tube 2 can be improved. At the same time, the locking hook 32 will not be blocked by the mounting part 22 of the inner push tube 2 when it is flipped.

[0075] In this embodiment, the outer peripheral wall of the gripping part 23 is spirally connected to a detachable knob sleeve, which makes it convenient for the operator to turn the inner push tube 2 to rotate, thereby driving the locking hook 32 of the pump body 31 to be implanted into the heart tissue.

[0076] Both the gripping part 23 and the main body part 21 are hollow circular tubes, ensuring that the space gap between the inner push tube 2 and the outer push tube is small, reducing the overall size of the entire system and reducing the difficulty of postoperative recovery.

[0077] In this embodiment, as Figure 1 As shown, the end of the outer tube 1 that extends into the left ventricle 41 is also provided with a hook release slit 11;

[0078] The shape and number of the hook release slots 11 are adapted to the shape and number of the locking hooks 32;

[0079] A spring is fitted on the connecting shaft of the locking hook 32. The spring is a torsion spring, with one end of the torsion spring located on the pump body 31 and the other end located on the locking hook 32.

[0080] By setting the hook release slot 11 and fitting a torsion spring on the connecting shaft of the locking hook 32, the pump body assembly 3 is pushed into the left ventricle 41 through the inner push tube 2. When most of the pump body 31 is still inside the outer tube 1, the locking hook 32 can be in the unfolded state. This allows the inner push tube 2 to drive the pump body 31 to rotate while most of the pump body 31 is still inside the outer tube 1, thereby inserting the locking hook 32 of the pump body 31 and fixing the pump body 31. This prevents the inner push tube 2 from extending out of the outer tube 1, which could cause the pump body assembly 3 to accidentally fall off during locking.

[0081] In this embodiment, the outer tube 1 includes a restricted rotation section and a free rotation section;

[0082] The outer tube 1 has a strip-shaped protrusion 13 arranged parallel to its axial direction in the restricted rotation section;

[0083] The outer peripheral wall of the inner push tube 2 is fixed with a notch structure 24 that matches the strip protrusion 13;

[0084] With the recessed structure 24 of the inner push tube 2 fastened to the strip protrusion 13, the relative rotation between the inner push tube 2 and the outer tube 1 is restricted.

[0085] With the recessed structure 24 of the inner push tube 2 detached from the strip protrusion 13, the inner push tube 2 and the outer tube 1 can rotate freely relative to each other.

[0086] like Figure 2As shown, a strip-shaped protrusion 13 is provided inside the outer tube 1, and a notch structure 24 is provided on the outer peripheral wall of the inner push tube 2. When the notch structure 24 of the inner push tube 2 is fastened to the strip-shaped protrusion 13, the inner push tube 2 can only move back and forth in the outer tube 1 along its axis. After the pump body assembly 3 is installed into the mounting part 22 of the inner push tube 2, the locking hook 32 on the pump body 31 and the inner push tube 2 will no longer rotate relative to each other. Similarly, by using the strip-shaped protrusion 13 and the notch structure 24, the inner push tube 2 and the outer tube 1 can be prevented from rotating relative to each other. At this time, when the pump body assembly 3 is pushed into the left ventricle 41 by the inner push tube 2, when most of the area of ​​the pump body assembly 3 is inside the outer tube 1, the locking hook 32 on the pump body 31 can be opened in advance through the hook release slot 11. Thus, when part of the pump body 31 is still inside the outer tube 1, the inner push tube 2 can be rotated, thereby implanting the locking hook 32 on the pump body 31 into the heart tissue.

[0087] In this embodiment, the end of the outer tube 1 that extends into the left ventricle 41 is also provided with a limiting protrusion 12 for limiting the extension length of the inner push tube 2, thereby limiting the maximum length of the inner push tube 2 moving into the left ventricle 41. In this embodiment, the notch structure 24 provided on the outer peripheral wall of the inner push tube 2 can be used in conjunction with the limiting protrusion 12 to limit the maximum dislodgement distance of the inner push tube 2. In specific applications, the maximum dislodgement distance of the inner push tube 2 can also be used, and the length of the outer tube 1 extending into the left ventricle 41 can be checked before implanting the outer tube 1. When the notch structure 24 of the inner push tube 2 moves to the limiting protrusion 12, the position of the pump assembly 3 is the ideal implantation position, thereby providing the surgeon with a structural plan for the implantation position and reducing surgical pressure.

[0088] In some embodiments, the pump assembly 3 further includes a guide wire hole ring 36 disposed on the side wall of the pump body 31, and a guide wire (not shown in the figure) for guiding the pump assembly 3. The guide wire is inserted into the guide wire hole ring 36, so that the surgeon can insert the guide wire into place first when performing the operation. When implanting the pump assembly 3, the guide wire can be used to guide the pump assembly 3 into place, so that the internal push tube 2 can push the pump assembly 3 to the position of the guide wire end, which is convenient for the surgeon to operate. After the pump assembly 3 is installed in place, the guide wire can be pulled out.

[0089] It is understood that the above embodiments are merely exemplary embodiments used to illustrate the principles of the present invention, and the present invention is not limited thereto. For those skilled in the art, various modifications and improvements can be made without departing from the spirit and essence of the present invention, and these modifications and improvements are also considered to be within the scope of protection of the present invention.

Claims

1. A transapical implantable system for a cardiac assist pump, characterized in that, include: An outer tube (1) for establishing an implantation channel, an inner tube (2) located inside the outer tube (1), and a pump assembly (3) installed at the end of the inner tube (2), wherein: The pump body assembly (3) includes a pump body body (31) and a plurality of locking hooks (32) connected to the pump body body (31). The locking hook (32) has a bent embedding section (321) for embedding into heart tissue at one end away from the pump body (31). The bent embedding sections (321) of the multiple locking hooks (32) are all bent or bent along the circumference of the pump body (31). The pump body (31) is provided with a first rotation limiting structure, and the end of the inner push tube (2) is provided with a second rotation limiting structure. The pump body assembly (3) and the inner push tube (2) rotate synchronously with each other through the mutually adapted first and second rotation limiting structures. The outer tube (1) is also provided with a hook release slit (11) at one end that extends into the left ventricle (41). The shape and number of the hook release slots (11) are adapted to the shape and number of the locking hooks (32); A spring is fitted on the connecting shaft of the locking hook (32), with one end of the spring located on the pump body (31) and the other end located on the locking hook (32); The outer tube (1) includes a restricted rotation section and a free rotation section; The outer tube (1) has a strip-shaped protrusion (13) arranged parallel to its axial direction in the restricted rotation section. The outer peripheral wall of the inner push tube (2) is fixed with a notch structure (24) that matches the strip protrusion (13). With the notch structure (24) of the inner push tube (2) fastened to the strip protrusion (13), the relative rotation between the inner push tube (2) and the outer tube (1) is restricted; With the concave structure (24) of the inner push tube (2) detached from the strip protrusion (13), the inner push tube (2) and the outer tube (1) can rotate freely relative to each other.

2. The transapical implantable cardiac assist pump system according to claim 1, characterized in that, The pump body assembly (3) also includes a blade mounting base (33) disposed on the output end of the pump body body (31) and a blade structure (34) mounted on the blade mounting base (33).

3. The transapical implantable cardiac assist pump system according to claim 2, characterized in that, The blade structure (34) is movably connected to the blade mounting base (33); The blade mounting base (33) is provided with multiple movable connection slots (331) on its top. The blade structure (34) includes a fixedly connected blade body (341) and blade seat (342), and the blade body (341) is movably connected to the movable connecting groove (331) through the blade seat (342).

4. The transapical implantable cardiac assist pump system according to claim 3, characterized in that, It also includes a locking assembly (35), which is located at the bottom of the blade seat (342); The side of the movable connecting groove (331) is also provided with a locking triangular groove (332) for cooperating with the locking assembly (35). The locking assembly (35) includes a top pressure spring (351) and a T-shaped locking rod (352) movably connected to the bottom of the blade seat (342). One end of the top pressure spring (351) presses against the T-shaped locking rod (352), and the other end presses against the blade seat (342).

5. The transapical implantable cardiac assist pump system according to claim 1, characterized in that, The first rotation limiting structure is a rotation limiting groove (311), the bottom of which extends to the bottom of the pump body (31); The second rotation limiting structure is a rotation limiting protrusion (223) located at the end of the inner push tube (2), and the width of the rotation limiting protrusion (223) is the same as the width of the rotation limiting groove (311).

6. The transapical implantable cardiac assist pump system according to claim 1, characterized in that, The inner push tube (2) includes a main body (21), and a gripping part (23) and a mounting part (22) located at both ends of the main body (21). The total length of the inner tube (2) is greater than the length of the outer tube (1); The mounting part (22) is provided with a placement plate (221) at one end near the main body part (21), and the placement plate (221) is also provided with a wire hole (224). A baffle (222) extends upward from the top of the mounting part (22), and the first rotation limiting structure is provided on the baffle (222) and extends to the bottom of the mounting part (22).

7. The transapical implantable cardiac assist pump system according to claim 1, characterized in that, The bent insert section (321) of the locking hook (32) is also provided with several barbed structures (322) or abutting structures.

8. The transapical implantable system for a cardiac assist pump according to claim 1, characterized in that, The outer tube (1) is also provided with a limiting protrusion (12) at one end that extends into the left ventricle (41) to limit the extension length of the inner push tube (2).

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