Extrusion nail for orthopedics and assembly thereof

Abstract

The application provides a kind of extrusion nail and its assembly for orthopedics, which is applied to the technical field of orthopedic surgical instruments.The extrusion nail adopts a threadless structure and is composed of a nail body, a barb and an extrusion groove, and can be adapted to different length bone tunnels through the head-to-tail matching of multiple nails.The assembly includes an execution end and an impact handle, which can provide linear impact force to realize the linear implantation of the extrusion nail.The application replaces the rotary screwing with linear advancement, fundamentally avoiding the shearing and torsional injury of ligaments, and has the advantages of precise implantation, convenient operation and stable fixation, which meets the clinical needs of orthopedic ligament reconstruction surgery and improves the safety of surgery and the quality of postoperative healing.

Description

Technical Field

[0001] This application relates to the field of orthopedic surgical instruments, and in particular to an orthopedic compression screw and its assembly. Background Technology

[0002] In orthopedic ligament reconstruction surgery, the fixation effect between the transplanted ligament and the bone tunnel directly determines the quality of postoperative healing, and compression screws are the core instruments for this procedure.

[0003] Currently, most compression pins used in clinical practice are screw-shaped, which achieve fixation by rotating and screwing them in. However, the threads of these screw-shaped compression pins are helical, and during screwing, the threads exert continuous shear and torsional forces on the ligaments within the bone tunnel. Ligament tissue is mainly composed of collagen fibers, which are fragile and have poor torsional resistance. The helical shear force can directly lead to ligament fiber rupture and disordered arrangement, destroying the mechanical integrity of the ligament. At the same time, the torsional force can pull on the interface between the ligament and the bone tunnel, affecting the postoperative healing and adhesion between the ligament and bone tissue.

[0004] Meanwhile, the threaded grooves of the screw-shaped compression pins create a suction effect when rotating, which can easily pull the fibers at the edge of the ligament into the threaded gap, causing local tearing and defects of the ligament. If the pull-in depth is deep, additional ligament dissection is required during the operation, which can further expand the scope of damage and prolong the operation time.

[0005] Therefore, we propose an orthopedic compression screw and its assembly to solve the above problems. Summary of the Invention

[0006] The purpose of this application is to address the technical problem that existing screw-shaped compression pins are prone to causing ligament damage during the screwing process. Compared with the prior art, this application provides an orthopedic compression pin that is suitable for impact-type implantation into a bone tunnel. The compression pin consists of a pin body and barbs. The pin body includes, from bottom to top, a cylinder, a frustum, and a conical guide head. A number of barbs are arranged in an array on the outer wall of the pin body. The side of the pin body away from the barbs is provided with a compression groove for compressing the ligament.

[0007] The nail body is also provided with a guide wire hole for inserting a guide wire;

[0008] The nail body is provided with a mating groove and a C-shaped groove on the side away from the tapered guide head, and the inner contour of the mating groove matches the outer contour of the tapered guide head.

[0009] Within the bone tunnel, multiple sets of compression nails, connected end to end, can be sequentially implanted by engaging the mating groove and the conical guide head.

[0010] Furthermore, the extrusion groove includes an equal-diameter groove disposed on the cylinder and a variable-diameter groove disposed on the frustum and the conical guide head. The axis of the equal-diameter groove is equal to the axis of the guide wire hole, and the axis of the variable-diameter groove gradually increases from bottom to top with respect to the axis of the guide wire hole.

[0011] After the two sets of extrusion pins are aligned with the conical guide head through the mating groove, the equal diameter groove and the variable diameter groove cooperate to form an extrusion boss, which creates a stepped extrusion for the ligaments in the bone tunnel.

[0012] Furthermore, the barbs are symmetrically provided with guide sidewalls on both sides, the vertical distance between the two sets of guide sidewalls gradually decreases along the direction close to the conical guide head, and the horizontal distance between the two sets of guide sidewalls gradually decreases along the direction close to the axis of the guide wire hole.

[0013] Flat-head teeth are provided between the bottoms of the two sets of guide sidewalls away from the conical guide head.

[0014] Furthermore, the distance between the barb and the guide wire hole axis gradually decreases from the barb furthest from the extrusion groove to the barb closest to the extrusion groove, in order to prevent the extrusion pin from rotating circumferentially during the impact.

[0015] Furthermore, the inner wall of the extrusion groove is a smooth surface or a friction surface with blunt nail-like protrusions.

[0016] Furthermore, the extrusion pin has a hollow or solid structure, and the material of the extrusion pin is selected from at least one material selected from titanium-based ceramics, pure titanium, magnesium, tantalum and magnesium alloys.

[0017] The present invention also provides an assembly for an orthopedic compression screw, the assembly being used to force the compression screw into a bone tunnel, the assembly including an actuating rod, one end of the actuating rod being provided with an actuating end, the actuating end including an abutting protrusion that mates with a mating groove, a C-shaped protrusion that mates with a C-shaped groove, and a notch that mates with a compression groove;

[0018] The other end of the actuator is provided with a limiting platform and a handhold. The handhold is rotatably connected to the end of the actuator, and the limiting platform is fixed to the middle of the actuator. An impact handle is slidably connected between the limiting platform and the handhold, and the impact handle has a built-in counterweight.

[0019] The actuator is also provided with a second guide hole that is compatible with the first guide hole of the extrusion pin and is used to insert the guide wire.

[0020] Furthermore, a cross-shaped limiting groove is provided on the side of the limiting platform opposite to the impact handle, and a cross-shaped protrusion that matches the cross-shaped limiting groove is fixed on the impact handle.

[0021] Furthermore, the impact handle is used to impact the limiting platform under external force, using inertia to cause the actuator end to abut against the extrusion pin and strike the extrusion pin to advance into the bone tunnel on the knee joint;

[0022] The barbs are used to impact and create a straight groove for propulsion on the inner wall of the bone tunnel. After the impact handle is engaged with the limiting platform, the actuator rod and the actuator end are rotated by holding the hand seat and rotating the impact handle, thereby causing the barbs to rotate circumferentially relative to the straight groove for propulsion, forming a bidirectional contact limiting in the axial direction of the bone tunnel.

[0023] Compared to existing technologies, the advantages of this application are:

[0024] The extrusion pin of this invention uses a striking linear advancement method instead of a screw-like rotating insertion. The pin body has no thread structure, and no shearing or torsional force is generated during advancement, thus structurally eliminating the possibility of ligament fiber rupture or entanglement damage. With the guidance of the guide wire hole and the guide wire, the extrusion pin is ensured to advance precisely along the axis, avoiding eccentric compression damage to the ligament, and is suitable for the clinical needs of minimally invasive and precise surgery.

[0025] It can achieve end-to-end alignment of multiple compression screws without the need for custom compression screws of different lengths, and can flexibly adapt to bone tunnels of different lengths; the alignment process is linear, reducing surgical operation steps, lowering the risk of repeated ligament disturbance, and reducing the cost of preparing surgical instruments. Attached Figure Description

[0026] Figure 1 This is a front structural diagram of the extrusion nail proposed in this application;

[0027] Figure 2 This is a schematic diagram of the side structure of the extrusion nail proposed in this application;

[0028] Figure 3 This is a schematic diagram of the bottom structure of the extrusion nail proposed in this application;

[0029] Figure 4 This is a schematic diagram of the front structure of the barbs proposed in this application;

[0030] Figure 5 for Figure 4 Enlarged structural diagram of section A in the middle;

[0031] Figure 6 This is a schematic diagram of the bottom surface structure of the barbs proposed in this application;

[0032] Figure 7 This is a schematic diagram of the bottom structure of the assembly proposed in this application;

[0033] Figure 8 This is a front structural diagram of the assembly proposed in this application;

[0034] Figure 9 for Figure 8 Enlarged structural diagram of section B in the middle;

[0035] Figure 10 This is a schematic diagram showing the state of the assembly proposed in this application being used in conjunction with a single extrusion screw to penetrate the bone tunnel;

[0036] Figure 11 This is a schematic diagram showing the state of the assembly proposed in this application working with multiple sets of extrusion screws to penetrate the bone tunnel;

[0037] Figure 12 This is a schematic diagram showing the assembly fixture proposed in this application and multiple sets of extrusion pins in a sequential extrusion fit.

[0038] Figure 13 for Figure 12 Enlarged structural diagram of section C;

[0039] Figure 14 This is a cross-sectional structural diagram of the assembly fixture proposed in this application when it is sequentially pressed together with multiple sets of extrusion pins.

[0040] Figure 15 This is a schematic diagram showing the state of the impact handle when it impacts the extrusion nail as proposed in this application;

[0041] Figure 16 This is a schematic diagram showing the state of the impact handle when rotating to compress the pin, as proposed in this application.

[0042] Figure 17 This is a schematic diagram showing the before and after states of the barb as it rotates within the bone tunnel, as proposed in this application.

[0043] Explanation of the labels in the diagram:

[0044] 1. Extrusion pin; 11. Pin body; 111. Cylindrical body; 112. Frustum; 113. Conical guide head; 12. Guide wire hole one; 13. Barb; 131. Guide sidewall; 132. Flat tooth; 14. Extrusion groove; 1401. Extrusion boss; 141. Variable diameter groove; 142. Equal diameter groove; 15. C-groove; 16. Mating groove;

[0045] 2. Assembly fixture; 21. Actuating rod; 22. Limiting platform; 221. Cross-shaped limiting groove; 23. Impact handle; 231. Cross-shaped protrusion; 24. Handhold; 25. Actuating end; 251. C-shaped protrusion; 252. Abutting protrusion; 253. Notch groove; 254. Guide wire hole two;

[0046] 3. Knee joint; 301. Bone tunnel; 302. Advancement groove;

[0047] 4. Ligaments;

[0048] 5. Guide wire. Detailed Implementation

[0049] The embodiments will be described clearly and completely with reference to the accompanying drawings. All other embodiments obtained by those skilled in the art based on the embodiments in this application without creative effort are within the scope of protection of this application.

[0050] Example:

[0051] This invention provides an orthopedic compression screw and its assembly. Please refer to [link / reference]. Figure 1 - Figure 17 It is suitable for impact implantation into bone tunnel 301, and its core design is a threadless linear propulsion structure, thereby eliminating rotational damage.

[0052] For details, please refer to Figure 1 - Figure 6 The compression nail 1 consists of a nail body 11 and barbs 13. It should be noted that, in this embodiment, the compression nail 1 is preferably made of tantalum metal. The nail body 11 includes, from bottom to top, a cylinder 111, a frustum 112, and a conical guide head 113. The conical guide head 113 has a smooth conical structure, which can easily penetrate the soft tissue at the entrance of the bone tunnel 301, reduce the initial implantation resistance, and avoid ligament traction damage caused by rough implantation. The frustum 112 achieves a smooth diameter transition, avoids jamming during implantation, and reduces the instantaneous impact on the ligament. The cylinder 111 ensures the structural stability of the middle section of the compression nail 1 and forms a stable surface contact compression with the ligament 4, avoiding excessive local pressure. The nail body 11 uses a smooth outer wall in conjunction with the barbs 13 for fixation, avoiding damage from thread rotation.

[0053] Several barbs 13 are evenly arranged in an array along the axial direction of the nail body 11 on the outer wall of the nail body 11. The axial spacing between adjacent barbs 13 is 2-3 mm, which is adapted to the density of trabecular bone in the inner wall of the adult bone tunnel. This avoids insufficient fixation due to excessive spacing and damage to the bone wall due to insufficient spacing. The barbs 13 are impact-embedded integrated structures that are seamlessly formed with the nail body 11. They have no spiral guide design and are only used for contact fixation with the bone wall after implantation. They do not participate in the advancement process.

[0054] Furthermore, guide sidewalls 131 are symmetrically provided on both sides of the barb 13. The angle between the guide sidewalls 131 and the vertical axis of symmetry of the nail body 11 is 15-20°, which can effectively guide and prevent rotation, and will not increase the implantation resistance due to excessive angle. The vertical spacing of the two sets of guide sidewalls 131 gradually decreases along the direction close to the conical guide head 113, and the horizontal spacing gradually decreases along the direction close to the axis of the guide wire hole 12, forming a converging guide channel.

[0055] Flat-headed teeth 132 are provided between the bottoms of the two sets of guide sidewalls 131 away from the conical guide head 113. The flat-headed teeth 132 can prevent sharp edges from cutting bone tissue and ligaments, and the width of the flat-headed teeth 132 is consistent with the bottom width of the guide sidewalls 131, ensuring uniform force during impact embedding.

[0056] Please refer to this first. Figure 3 The nail body 11 has a compression groove 14 for compressing the ligament 4 on the side away from the barb 13, and the cross section of the compression groove 14 is shallow arc-shaped.

[0057] The compression groove 14 can be a smooth curved surface structure to reduce frictional damage when in contact with ligaments. The radius of curvature of the curved surface is 3-5mm, which is suitable for the diameter of commonly used transplanted ligaments, such as the diameter of the cruciate ligament of the knee joint, which is 4-6mm.

[0058] When the extrusion groove 14 is a friction surface with blunt nail-shaped protrusions, the protrusion height is 0.3-0.5mm, the protrusions are hemispherical, and they are evenly distributed along the axial direction of the extrusion groove 14. This can increase the friction with the ligament to prevent relative sliding, and will not puncture the ligament fibers.

[0059] The nail body 11 is provided with a guide wire hole 12 for inserting the guide wire 5; the guide wire hole 12 cooperates with the guide wire 5 to ensure that the pressing nail 1 advances in a straight line throughout the entire process without rotation or deviation.

[0060] Please refer to this first. Figure 3 The nail body 11 has a mating groove 16 and a C-shaped groove 15 on the side away from the conical guide head 113. The mating groove 16 is a conical countersunk hole structure, and the taper of the countersunk hole is consistent with the taper of the conical guide head 113. The mating groove 16 has a groove corresponding to the compression groove 14 on the conical guide head 113. During mating, rotation is avoided, thus maintaining the same direction of the compression grooves 14 on the two sets of nail bodies 11. This ensures accurate mating and avoids mating difficulties caused by interference fit. The opening angle of the C-shaped groove 15 is 120°, and the groove width is a transition fit with the width of the C-shaped protrusion 251 of the assembly 2 to achieve circumferential positioning, ensure that the impact force is transmitted axially, and facilitate the quick assembly and disassembly of the assembly and the compression nail. Through the mating of the mating groove 16 and the conical guide head 113, multiple sets of compression nails 1 can be implanted into the bone tunnel 301 end to end without the need for rotation and position adjustment.

[0061] An assembly 2 is provided for the aforementioned extrusion nail 1, providing a linear striking force to the extrusion nail 1, replacing the rotational screwing force of the screw-like extrusion nail.

[0062] For details, please refer to the following first. Figure 7 - Figure 17The assembly 2 includes an actuator 21, one end of which is provided with an actuator end 25. The actuator end 25 includes a contact protrusion 252 adapted to the mating groove 16, a C-shaped protrusion 251 adapted to the C-shaped groove 15, and a notch 253 adapted to the extrusion groove 14. The actuator end 25 is adapted to the extrusion nail 1 through multiple structures to ensure that the impact force is transmitted evenly along the axial direction and to prevent the extrusion nail 1 from being deviated by force.

[0063] The other end of the actuator 21 is provided with a limiting platform 22 and a handhold 24. The handhold 24 is rotatably connected to the end of the actuator 21. The actuator 21 is slidably connected between the limiting platform 22 and the handhold 24 with an impact handle 23 with a built-in counterweight. The impact handle 23 generates linear thrust through sliding impact, replacing rotational torque and completely avoiding ligament torsion damage.

[0064] The actuator 21 is provided with a second guide hole 254 that is adapted to the first guide hole 12; the first guide hole 12 and the second guide hole 254 are coaxially matched to form a double guide, ensuring that the extrusion nail 1 is pushed forward in a straight line throughout the entire process.

[0065] The limiting platform 22 is provided with a cross-shaped limiting groove 221, and the impact handle 23 is provided with a matching cross-shaped protrusion 231. This structure is only activated when the barb is rotated after implantation, and the rotation action is independent of the advancement process, avoiding ligament damage caused by simultaneous advancement and rotation.

[0066] This invention avoids ligament shearing and torsional damage throughout the entire process through step-by-step operations including guided positioning, impact implantation, multi-screw alignment, and rotational limiting.

[0067] During the surgery, a bone tunnel 301 is pre-drilled in the knee joint 3, and then the ligament 4 and guide wire 5 are sequentially inserted. The two ends of the ligament 4 are fixed to the outer wall of the knee joint 3. At this time, the compression nail 1 with guide wire hole 12 and the assembly 2 with guide wire hole 254 are sequentially inserted into the guide wire 5 to ensure that the two are coaxial. Then, the abutting protrusion 252 of the execution end 25 is inserted into the mating groove 16, and the C-shaped protrusion 251 is inserted into the C-shaped groove 15, so that the notch groove 253 is aligned with the compression groove 14.

[0068] At this time, the handheld base 24 of the handheld assembly 2 aligns the conical guide head 113 of the compression nail 1 with the entrance of the bone tunnel 301, and keeps the ligament 4 in the bone tunnel 301 covered within the compression groove 14; the handheld base 24 slides back and forth along the actuator rod 21 to impact the handle 23, and uses the inertia of the counterweight to impact the limiting platform 22, so that the actuator end 25 transmits axial linear thrust to the compression nail 1, pushing the compression nail 1 forward at a constant speed along the guide wire 5. During the entire advancement process, the compression nail 1 does not rotate, and the smooth outer wall of the nail body 11 only makes surface contact with the ligament 4 for compression, without shearing force; the guide side wall 131 of the barb 13 guides the compression nail 1 to be stably implanted, avoiding displacement and compression of the ligament 4; the flat teeth 132 only embed into the bone wall under the impact, forming temporary fixation, without rotational cutting action.

[0069] When secondary fixation is required, after the first compression nail 1 is implanted to the predetermined depth, the guide wire hole 12 of the second compression nail 1 is directly inserted into the guide wire 5, so that the mating groove 16 of the second nail 1 aligns with the conical guide head 113 of the first nail 1; the striking operation is repeated to make the two compression nails 1 align end to end to form a whole. This design can flexibly increase or decrease the number of compression nails according to the length of the bone tunnel 301 without the need to customize instruments of different lengths; and the alignment process is a linear advancement without rotational adjustment, avoiding disturbance and damage to the ligament 4 during secondary operation.

[0070] After all the compression pins 1 are implanted, a rotational limiting operation is performed. The handheld base 24 is kept fixed, and the impact handle 23 is rotated. Through the cooperation of the cross-shaped protrusion 231 and the cross-shaped limiting groove 221, the actuator 21 and the compression pins 1 rotate synchronously. The barbs 13 rotate within the advancement groove 302 on the inner wall of the bone tunnel 301, so that the flat teeth 132 of the barbs 13 form bidirectional contact with the bone wall. Since this rotational action is performed after the compression pins 1 are fully implanted, the compression pins 1 and the ligament 4 have formed a stable surface contact compression. The rotation angle is small, usually not exceeding the width of the barbs 13, and will not generate significant shear force on the ligament 4, completely different from the injury mode of the rotational advancement of screw-shaped compression pins.

[0071] For more specific details, please refer to [the relevant documentation]. Figure 17 The core of this application is a composite fixation mechanism of "impact implantation + bidirectional resistance after slight rotation". The propulsion groove 302 is only a temporary guide channel before rotation, and it is transformed into a fixed limiting structure after rotation. The specific logic is as follows:

[0072] Impact Phase: During the impact-driven implantation of the temporary fixation compression pin 1, the guide sidewall 131 of the barb 13 impacts the inner wall of the bone tunnel, forming a propulsion groove 302. The function of this propulsion groove 302 is: ① to guide the compression pin 1 along a straight line, avoiding circumferential rotation during implantation; ② to embed the flat-headed teeth 132 of the barb 13 into the sidewall of the propulsion groove 302, forming preliminary axial positioning and preventing the compression pin 1 from springing back during implantation. At this time, the propulsion groove 302 is a "one-way guiding structure," but it is not the core upon which the final fixation depends.

[0073] Rotation stage: The straight groove 302 is transformed into a bidirectional limiting groove. After all the extrusion pins 1 are inserted, the extrusion pins 1 are rotated by the assembly 2 (rotation angle ≤ barb width), and the barbs 13 are circumferentially offset relative to the straight groove 302.

[0074] One side guide wall 131 of the barb 13 is in close contact with one side wall of the propulsion groove 302, forming a limit on the "forward direction";

[0075] The barbed flat-headed teeth 132 are embedded in the bone on the other side wall of the straight groove 302, forming a reverse contact in the "exit direction";

[0076] Ultimately, a "two-way jamming" limiting structure is formed. At this time, the push straight groove 302 is no longer a "through guide channel" but a "serrated fixing groove" that engages with the barb 13. The path of the extrusion nail 1 exiting along the push straight groove 302 is completely blocked, which can effectively prevent the extrusion nail 1 from retracting and improve the stability of the installation.

[0077] After multiple compression pins 1 are aligned, the equal-diameter groove 142 and the variable-diameter groove 141 cooperate to form a continuous compression boss 1401, which forms a stepped and uniform compression on the ligament 4 within the bone tunnel 301. This compression method disperses the force on the ligament to multiple boss contact points, avoiding local stress concentration; at the same time, the compression boss 1401 is a smooth curved surface that makes surface contact with the ligament 4, eliminating the risk of cutting and further protecting the integrity of the ligament fibers.

[0078] The extrusion nail 1 of this invention adopts a striking linear advancement method instead of a screw-like rotating screw-in method. The nail body 11 has no thread structure, and no shearing or torsional force is generated during advancement, which structurally eliminates the possibility of ligament fiber rupture or entanglement damage. With the guidance of the guide wire hole 12 and the guide wire 5, it ensures that the extrusion nail 1 is accurately advanced along the axis, avoiding eccentric compression damage to the ligament, and is suitable for the clinical needs of minimally invasive and precise surgery.

[0079] Multiple compression screws 1 can be aligned end to end without the need to customize compression screws 1 of different lengths, and can be flexibly adapted to bone tunnels 301 of different lengths; the alignment process is a linear advancement, reducing surgical operation steps, reducing the risk of repeated disturbance of ligaments 4, and reducing the cost of preparing surgical instruments.

[0080] The above are merely the best implementation methods adopted in this application in light of current practical needs, but the scope of protection of this application is not limited thereto.

Claims

1. An orthopedic compression screw (1) suitable for impact-type implantation into a bone tunnel (301), characterized in that, The compression nail (1) is composed of a nail body (11) and barbs (13). The nail body (11) includes a cylinder (111), a frustum (112) and a conical guide head (113) from bottom to top. A number of barbs (13) are arranged in an array on the outer wall of the nail body (11). The side of the nail body (11) away from the barbs (13) is provided with a compression groove (14) for compressing the ligament (4). The nail body (11) is also provided with a guide wire hole (12) for inserting the guide wire (5). The nail body (11) is provided with a mating groove (16) and a C-shaped groove (15) on the side away from the conical guide head (113), and the inner contour of the mating groove (16) matches the outer contour of the conical guide head (113). The bone tunnel (301) can be used to implant multiple sets of compression nails (1) in sequence by engaging the mating groove (16) and the conical guide head (113). The extrusion groove (14) includes an equal-diameter groove (142) disposed on the cylinder (111) and a variable-diameter groove (141) disposed on the frustum (112) and the conical guide head (113). The axis of the equal-diameter groove (142) is spaced from the axis of the guide wire hole (12), and the axis of the variable-diameter groove (141) gradually increases from bottom to top with respect to the axis of the guide wire hole (12). After the two sets of extrusion nails (1) are engaged with the conical guide head (113) through the mating groove (16), the equal diameter groove (142) and the variable diameter groove (141) cooperate to form an extrusion boss (1401), which forms a stepped extrusion for the ligament (4) in the bone tunnel (301); The barb (13) is provided with symmetrical guide sidewalls (131) on both sides. The vertical distance between the two sets of guide sidewalls (131) gradually decreases along the direction close to the conical guide head (113), and the horizontal distance between the two sets of guide sidewalls (131) gradually decreases along the direction close to the axis of the guide wire hole (12). Flat-headed teeth (132) are provided between the bottoms of the two sets of guide sidewalls (131) away from the conical guide head (113). From the barb (13) furthest from the extrusion groove (14) to the barb (13) closest to the extrusion groove (14), the distance between the barb (13) and the axis of the guide wire hole (12) gradually decreases to prevent the extrusion nail (1) from rotating circumferentially during the impact.

2. The orthopedic compression screw according to claim 1, characterized in that, The inner wall of the extrusion groove (14) is a smooth surface or a friction surface with blunt nail-shaped protrusions.

3. The orthopedic compression screw according to claim 2, characterized in that, The extrusion nail (1) is a hollow or solid structure, and the material of the extrusion nail (1) is selected from at least one of titanium-based ceramics, pure titanium, magnesium, tantalum and magnesium alloys.

4. An assembly for an orthopedic compression screw, applicable to the orthopedic compression screw of claim 3, wherein the assembly (2) is used to force the compression screw (1) into the bone tunnel (301), characterized in that, The assembly (2) includes an actuating rod (21), one end of which is provided with an actuating end (25). The actuating end (25) includes an abutting protrusion (252) that engages with the mating groove (16), a C-shaped protrusion (251) that engages with the C-shaped groove (15), and a notch (253) that engages with the extrusion groove (14). The other end of the actuator (21) is provided with a limiting platform (22) and a handheld base (24). The handheld base (24) is rotatably connected to the end of the actuator (21). The limiting platform (22) is fixed to the middle of the actuator (21). An impact handle (23) is slidably connected between the limiting platform (22) and the handheld base (24) of the actuator (21). The impact handle (23) has a built-in counterweight. The actuator (21) is also provided with a second guide wire hole (254) that is adapted to the first guide wire hole (12) of the extrusion nail (1) and is used to insert the guide wire (5).

5. The assembly for an orthopedic compression screw according to claim 4, characterized in that, The limiting platform (22) is provided with a cross limiting groove (221) on the side opposite to the impact handle (23), and a cross protrusion (231) that matches the cross limiting groove (221) is fixed on the impact handle (23).

6. The assembly for an orthopedic compression screw according to claim 5, characterized in that, The impact handle (23) is used to impact the limiting platform (22) under external force, and use inertia to make the actuator (25) abut against the extrusion pin (1) and strike the extrusion pin (1) to advance in the bone tunnel (301) on the knee joint (3); The barb (13) is used to impact the inner wall of the bone tunnel (301) to create a straight groove (302). After the impact handle (23) is engaged with the limiting platform (22), the actuator (21) and the actuator end (25) are rotated by holding the hand seat (24) and rotating the impact handle (23), thereby causing the barb (13) to rotate circumferentially relative to the straight groove (302), forming a bidirectional contact limiting in the axial direction of the bone tunnel (301).

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