Osteotomy end repair prosthesis for amputation operation

Abstract

The invention relates to the technical field of amputation repair prostheses, and discloses an osteotomy end repair prosthesis for an amputation operation, which comprises a prosthesis implantation part arranged in a connecting bone above an osteotomy plane at an amputation position of a patient; the prosthesis bearing part is arranged at the end, away from the connecting bone, of the prosthesis implanting part, and one end of the prosthesis bearing part is fixedly connected with the prosthesis implanting part and makes contact with a bone osteotomy plane; wherein the outer surface structure of the prosthesis implanting part is a porous structure and is in contact with the inner surface of a marrow cavity of a connecting bone of the residual part of an amputation bone. Through the special structural design of the bearing part, the stress of the residual bone is dispersed to surrounding soft tissue, pain caused by the fact that the irregular osteotomy end directly stimulates the soft tissue is avoided, and therefore the bearing capacity and the gravity conduction capacity of the distal end of the residual limb are improved; the problems that an artificial limb socket is difficult to manufacture due to the fact that the stump cannot be stressed, and the use experience of a patient is poor due to the fact that the ischial tuberosity is stressed are solved. And the micro-pore design on the surface of the implantation part reduces the stress concentration and stress shielding effect of the bone tissue around the prosthesis, enhances the biological integration capability of the prosthesis and the bone tissue, and further reduces the risk of prosthesis failure.

Description

Technical Field

[0001] The invention relates to the technical field of amputation repair prostheses, and in particular to a prosthesis for repairing osteotomy ends in amputation surgery. Background Art

[0002] Amputation refers to the surgical removal of part or all of a limb. It is a relatively serious surgical procedure performed to save life, improve function or relieve unbearable pain.

[0003] Amputation surgery involves a wide range of surgical fields, such as war surgery, general surgery, vascular surgery, tumor surgery, burn surgery, plastic surgery and orthopedics. Almost every day, the emergency surgery departments of various hospitals perform amputations of various limbs. In recent years, the number of patients who have undergone amputation due to peripheral vascular disease or concurrent diabetes has increased, and it has become the primary cause of amputation, and is on the rise.

[0004] After amputation, the normal anatomical structure of the limb is partially missing, and the physiological function of the missing part is lost. The more parts are missing, the more physiological functions are lost, and the more serious the functional impairment is. Prostheses are artificial limbs specially made and assembled to make up for the limb defects of amputees and compensate for their lost limb functions.

[0005] The main functions of the lower limbs of the human body are standing, moving, walking, running, jumping, etc. The purpose of installing lower limb prostheses is to restore the lost normal appearance of the amputee as much as possible and to reconstruct the lost functions of standing, moving, walking, etc., but it can only compensate for part of the lost functions.

[0006] At present, the most widely used clinical prosthesis is the cavity-type prosthesis, in which the cavity bears the trunk gravity transmitted by the residual limb, and transmits the force to the ground through the prosthetic connector connected to it to achieve support. The prosthesis is composed of a receiving cavity, joints, connectors, prosthetic limbs and other parts. Among them, the receiving cavity is the part where the prosthesis connects to the residual limb, which plays the role of bearing weight, fixing and transmitting movement. When making it, it is required to fit closely with the shape of the residual limb to ensure comfort and stability.

[0007] According to the missing state of anatomical structure of limbs after amputation, it can be divided into foot amputation, ankle amputation, calf amputation, knee amputation, thigh amputation, hip amputation, etc. Among them, calf amputation and thigh amputation account for the majority. Except for ankle amputation and knee amputation, the distal end of the residual limb can hardly bear force. This brings great challenges to the production of prosthetic sockets.

[0008] The reason why the distal end of the residual limb cannot bear force is mainly because the osteotomy surfaces of the tibia, femur, fibula, etc. are irregular, which brings continuous mechanical stimulation to the surrounding soft tissues, causing pain. Even if the osteotomy surface can be finely modified during surgery, due to the special mechanical environment of the residual limb, the cross section will also undergo continuous and irregular bone tissue absorption, regeneration and reconstruction and other biological processes, ultimately leading to irregular osteotomy surfaces.

[0009] Therefore, it is necessary to design a buffer structure for repairing the osteotomy surface of amputation surgery to avoid the pain at the distal end of the residual limb caused by the continuous mechanical stimulation of the osteotomy surface. The buffer structure combines soft tissue reconstruction such as muscles with flap suture technology to simulate the effect of knee-dislocation amputation. The produced receiving cavity can realize the load-bearing of the distal end of the residual limb, thereby restoring the force conduction function of the residual end to the greatest extent. Especially for thigh amputation, the force conduction method with the ischial tuberosity as the main load-bearing part is changed to a force conduction method with the receiving cavity bearing the full weight, which can improve the patient's ability to control the prosthesis and reduce energy consumption during walking. Summary of the invention

[0010] In view of this, the present invention proposes a prosthesis for repairing the osteotomy end of amputation surgery, aiming to solve the problem that the distal end of the residual limb of the traditional socket prosthesis cannot bear weight and the force transmission method is unfavorable in actual use, which leads to difficulty in making the prosthetic socket and poor patient experience.

[0011] The present invention provides a prosthesis for repairing the osteotomy end of amputation surgery, comprising:

[0012] The prosthesis implant part is arranged inside the bone marrow cavity of the osteotomy stump of the patient;

[0013] A prosthesis supporting part is arranged at one end of the prosthesis implant part near the osteotomy surface, one end of the prosthesis supporting part is respectively fixedly connected to the prosthesis implant part and contacts the osteotomy surface;

[0014] Wherein, the outer surface structure of the prosthesis implant part is a porous structure.

[0015] Furthermore, the prosthesis implantation part comprises:

[0016] The support column is arranged at the center of the implant part and is a solid structure with a diameter of 6 to 10 mm and a length of 60 to 120 mm;

[0017] The porous structure layer of the implant is arranged outside the implant support column and is fixedly connected and fused with the support column as a whole. The outer side of the porous layer of the implant is in direct contact with the inner wall of the bone marrow cavity of the osteotomy end. The thickness of the porous structure layer is 1 to 3 mm, and the pore size ranges from 400 to 1000 mm. μm .

[0018] Furthermore, the contact portion between the implant part and the proximal end of the osteotomy end is a hemispherical structure, and the diameter thereof is adapted to the implant part and is 8 to 14 mm.

[0019] Furthermore, the prosthesis supporting part comprises:

[0020] A support body is arranged at one end of the implant part near the osteotomy plane, the support body is respectively connected to the implant part support column and the porous structure layer, and is in contact with the osteotomy end surface, and the cross-sectional diameter of the support body is 30 to 40 mm;

[0021] A buffer pad is arranged outside the supporting body, and the buffer pad is used to support the supporting body;

[0022] Wherein, the buffer pad is a curved surface structure, and the curvature of the curved surface is 60 to 300 mm.

[0023] Furthermore, the support column and the supporting body are an integrated structure.

[0024] Furthermore, the porous structure layer of the implant and the support column are an integrated structure, and the support body and the buffer pad are an integrated structure;

[0025] The materials of the implant part and the supporting part include but are not limited to titanium alloy, PEEK and other materials.

[0026] Compared with the prior art, the beneficial effect of the present invention is that the curved surface structural design of the prosthesis support part enables the distal end of the residual limb to have the function of conducting force. When the patient stands or walks, the prosthesis support part will evenly transfer the gravity of the residual bone to the soft tissue of the residual limb, and then transfer the force to the receiving cavity through the distal end of the residual limb, providing support for the trunk. Since the support part is located at the distal end of the prosthesis, the curved surface structural design can effectively disperse the pressure transmitted by the prosthesis to the soft tissue of the distal end of the residual limb. This curved surface design can avoid the stress concentration caused by the direct contact between the bone and soft tissue due to the irregular osteotomy surface. The contact surface area of ​​the prosthesis support part is larger than the area of ​​the simple osteotomy surface, so that more force can be transmitted through the distal end of the residual limb. The receiving cavity thus made can realize the load-bearing of the distal end of the residual limb, thereby restoring the force conduction function of the residual end to the greatest extent. After amputation surgery, patients usually experience femoral adduction, resulting in a deviation of the force line of the lower limb. The inclined surface design of the support part can improve the mechanical alignment of the residual limb, making it closer to the force line of the lower limb before amputation, and improving the efficiency of force conduction. By optimizing the force transmission path, the service life of the prosthesis is extended, and the patient's comfort and prosthesis control ability are also improved. In addition, by designing the prosthesis implant to be embedded in the bone marrow cavity of the patient's osteotomy end, and adopting a porous structure on its outer surface, the ability of the prosthesis to combine with bone tissue can be improved. The core principle of this design is that the porous structure can provide space for bone cells to grow into the prosthesis, enhancing the integration ability and bonding strength of the prosthesis bone. The appropriate pore size design of the porous structure can also promote the differentiation of stem cells into osteoblasts, thereby promoting bone regeneration and reconstruction. The porous structure also provides more bone cell attachment points, allowing bone cells to grow and aggregate rapidly on the surface of the prosthesis, promoting the regeneration and healing of bone tissue. This biological integration process is crucial for the long-term stability of the prosthesis and can effectively reduce the risk of postoperative prosthesis loosening. In addition, with the advantages of the porous structure, the prosthesis can establish a firm bond with the surrounding bone tissue more quickly after implantation, reducing the incidence of postoperative complications. Finally, through reasonable prosthesis geometry and material design, the prosthesis can achieve a more ideal force transmission efficiency, avoid prosthesis loosening due to stress shielding around the prosthesis, and improve the functional recovery level of amputees. BRIEF DESCRIPTION OF THE DRAWINGS

[0027] Various other advantages and benefits will become apparent to those of ordinary skill in the art by reading the detailed description of the preferred embodiments below. The accompanying drawings are only for the purpose of illustrating the preferred embodiments and are not to be considered as limiting the present invention. Moreover, the same reference symbols are used throughout the accompanying drawings to represent the same components. In the accompanying drawings:

[0028] Figure 1 A schematic diagram of the structure of a prosthesis for repairing osteotomy ends of amputation surgery provided by an embodiment of the present invention;

[0029] Figure 2A schematic diagram of the dissection of Example 1 provided in accordance with an embodiment of the present invention;

[0030] Among them, 100, prosthesis implant part; 200, prosthesis supporting part; 110, implant porous structure layer; 120, support column; 210, supporting body; 220, buffer pad. DETAILED DESCRIPTION

[0031] Exemplary embodiments of the present disclosure will be described in more detail below with reference to the accompanying drawings. Although exemplary embodiments of the present disclosure are shown in the accompanying drawings, it should be understood that the present disclosure can be implemented in various forms and should not be limited by the embodiments described herein. On the contrary, these embodiments are provided in order to enable a more thorough understanding of the present disclosure and to fully convey the scope of the present disclosure to those skilled in the art. It should be noted that, in the absence of conflict, the embodiments of the present invention and the features described in the embodiments can be combined with each other. The present invention will be described in detail below with reference to the accompanying drawings and in combination with the embodiments.

[0032] like Figure 1-Figure 2 As shown, in some embodiments of the present invention, a prosthesis for repairing the osteotomy end of amputation surgery is provided, comprising: a prosthesis implant part 100 and a prosthesis supporting part 200.

[0033] Specifically, the prosthesis implant part 100 is arranged inside the bone marrow cavity of the patient's osteotomy stump; the prosthesis supporting part 200 is arranged at one end of the prosthesis implant part 100 close to the osteotomy surface, and one end of the prosthesis supporting part 200 is fixedly connected to the prosthesis implant part 100 and contacts the osteotomy surface; wherein the outer surface structure of the prosthesis implant part 100 is a porous structure.

[0034] It can be seen that the prosthesis implant part 100 is designed to be placed inside the medullary cavity of the osteotomy stump of the patient. This design can make full use of the natural morphology of the medullary cavity so that the prosthesis can obtain good support in the bone. The medullary cavity provides a closed and stable environment, so that the prosthesis can better contact with the bone tissue and form a strong mechanical fixation, reducing the risk of displacement or loosening of the prosthesis during use. Secondly, the outer surface of the prosthesis implant part 100 adopts a porous structure design, which plays a key role in improving the biological integration ability of the prosthesis and bone tissue. The porous structure provides sufficient attachment and growth space for bone cells, which can promote the formation of a firm bone bridge on the surface of the prosthesis by bone tissue, thereby achieving biological fixation. This biological integration not only enhances the stability of the prosthesis, but also reduces the risk of prosthesis loosening or bone absorption caused by insufficient mechanical fixation. At the same time, the prosthesis support part 200 is located at one end of the prosthesis implant part 100 near the osteotomy surface, and through the fixed connection with the prosthesis implant part 100 and the contact with the osteotomy surface, the mechanical stability of the prosthesis when subjected to force is ensured. The function of the prosthesis support part 200 is to effectively conduct and disperse the load on the osteotomy surface, so that the external pressure and force can be evenly transmitted between the prosthesis and the bone through the support part. This design reduces the possibility of local excessive force and avoids bone tissue damage or prosthesis structure damage caused by stress concentration. Through the reasonable design of the force conduction path, the prosthesis can maintain a high load-bearing capacity during use and extend the service life of the prosthesis. The combination of the porous structure and the support part realizes the dual optimization of mechanical and biological integration. The porous implant part enhances the biological bonding strength between the prosthesis and the bone tissue, while the support part ensures the uniform distribution of external force. The two cooperate with each other, which can significantly improve the overall stability of the prosthesis and reduce the bone absorption problem caused by postoperative prosthesis loosening and stress concentration. In addition, this design enables the distal end of the residual limb to transmit more force, and the receiving cavity made thereby can realize the load-bearing of the distal end of the residual limb, thereby maximizing the restoration of the force conduction function of the residual end, which not only reduces the difficulty of prosthesis assembly, but also improves the patient's comfort and prosthesis control ability. Under high-intensity use conditions, the prosthesis can still provide sufficient support and durability, bringing patients a better rehabilitation experience. Finally, the design of the prosthesis also fully considers the biocompatibility and mechanical properties of the material. By selecting suitable materials for the implant and the support part, this design can achieve a good balance between mechanical strength and biointegration capabilities. The high elastic modulus of the material can maintain sufficient rigidity during force transmission, while the porous surface ensures that the bone tissue can be firmly combined with the prosthesis, reducing the occurrence of postoperative complications. This comprehensive design provides an effective solution for prosthesis implantation after amputation surgery and improves the long-term quality of life of patients.

[0035] Specifically, the prosthesis implant part 100 includes: a support column 120 and an implant porous structure layer 110. The support column 120 is arranged at the center of the implant part, is a solid structure, and is designed to have a diameter of 6 to 10 mm and a length of 60 to 120 mm; the implant porous structure layer 110 is arranged on the outside of the implant support column 120, and is fixedly connected and fused with the support column 120 as a whole. The outside of the implant porous layer is in direct contact with the inner wall of the bone marrow cavity at the osteotomy end, and the thickness of the porous structure layer is 1 to 3 mm, and the pore size range is 400 to 1000 μm.

[0036] Specifically, the contact portion between the implant and the proximal end of the osteotomy end is a hemispherical structure, and the diameter thereof is adapted to the implant, and is 8 to 14 mm.

[0037] It can be seen that the support column 120 is a solid structure, which provides the main mechanical support for the prosthesis. Its diameter and length are reasonably designed to ensure the stability and durability of the prosthesis at the osteotomy end. The porous structure layer 110 of the implant surrounds the outside of the support column 120 and is fixedly connected to the support column 120 to form a whole, which not only enhances the mechanical strength of the prosthesis, but also provides an ideal environment for the growth of bone tissue. The thickness and pore size of the porous structure are optimized to ensure that bone cells can grow on the porous surface and achieve effective biological integration, thereby enhancing the close integration of the prosthesis with the inner wall of the bone marrow cavity. At the same time, the prosthesis adopts a hemispherical design for the contact part of the prosthesis with the proximal end of the osteotomy end, which helps to reduce local stress concentration and provide better mechanical conduction and distribution, so that the prosthesis can maintain stability and efficient force conduction performance during long-term use.

[0038] It is understandable that the support column 120, as the core load-bearing component of the prosthesis, is designed as a solid structure and provides strong mechanical support capabilities. The diameter of the support column 120 is designed to be 6 to 10 mm, which ensures the stability and adaptability of the prosthesis at the osteotomy end. Different patients have different bone structures and physiological conditions. The adjustable design of the support column 120 can adapt to the conditions of various osteotomy ends, ensuring that the prosthesis can provide sufficient bearing capacity after implantation and avoiding loosening or displacement of the prosthesis due to external forces. Secondly, the porous structure layer 110 of the implant surrounds the outside of the support column 120 and is fixedly connected to the support column 120 to form a whole. This structural design not only enhances the overall stability of the prosthesis, but also uses the special structure of the porous layer to achieve the purpose of biological integration. The thickness of the porous structure layer is designed to be 1 to 3 mm, and it has been carefully optimized to ensure that it can provide sufficient growth space for bone tissue. The porous structure layer is in direct contact with the inner wall of the bone marrow cavity, and the presence of pores provides an ideal microenvironment for the attachment and growth of bone cells. Bone tissue can gradually penetrate these pores and form a close bond with the surface of the prosthesis, thereby greatly enhancing the biological fixation effect of the prosthesis and reducing the risk of postoperative prosthesis loosening or falling off. At the same time, by combining the porous structure layer with the support column 120, the prosthesis can provide strong mechanical support while forming a firm biological connection with the surrounding bone tissue. This design not only enhances the fixation strength of the prosthesis, but also avoids the stress shielding effect caused by the difference in stiffness between the prosthesis and the bone tissue. The stress shielding effect will cause the bone tissue to gradually absorb due to insufficient stress, thereby affecting bone reconstruction and prosthesis stability. The porous structure layer ensures the normal stress distribution of the bone tissue and promotes the healthy growth of the bone tissue by alleviating this effect. In addition, the part of the prosthesis implant 100 that contacts the proximal end of the osteotomy end is designed as a hemispherical structure, and its diameter is adapted to the implant part, ranging from 8 to 14 mm. The geometric shape of this hemispherical design helps to effectively disperse pressure and reduce local stress concentration. Stress concentration is one of the main causes of prosthesis damage and bone tissue damage. The hemispherical design can distribute the external forces from the patient's weight and activities more evenly between the prosthesis and the bone, thereby reducing the risk of damage to local bone tissue. This geometric design not only improves the mechanical stability of the prosthesis, but also increases the durability of the prosthesis when it is subjected to complex multi-axial loads.

[0039] Specifically, the prosthesis support part 200 includes: a support body 210 and a buffer pad 220. The support body 210 is arranged at one end of the implant part near the osteotomy plane, the support body 210 is respectively connected to the implant part support column 120 and the porous structure layer, and contacts the osteotomy end surface, and the cross-sectional diameter of the support body 210 is 30 to 40 mm; the buffer pad 220 is arranged outside the support body 210, and the buffer pad 220 is used to support the support body 210; wherein the buffer pad 220 is a curved surface structure, and the curvature of the curved surface is 60 to 300 mm.

[0040] It is understandable that the support body 210, as the main bearing part of the prosthesis, is arranged at one end of the implant part near the osteotomy plane, and is tightly connected to the support column 120 and the porous structure layer respectively. This connection method not only ensures the integrity of the support body 210 and other parts of the prosthesis, but also enables the support body 210 to stably bear the externally applied force. The support body 210 adopts a slope design. This structural design can improve the mechanical alignment change caused by the adduction of the femur after amputation, making it closer to the lower limb force line before amputation, and improving the force conduction efficiency. By optimizing the force conduction path, not only can the service life of the prosthesis be extended, but also the patient's comfort and prosthesis control ability are improved. The cross-sectional diameter of the support body 210 is 30 to 40 mm. Such a size design can provide sufficient contact area between the prosthesis and the osteotomy plane, ensure uniform distribution of external force, reduce local stress concentration, avoid excessive pressure on the osteotomy end surface, and thus reduce the risk of prosthesis loosening and bone tissue damage. Secondly, the curved surface design of the buffer pad 220 is another key element of the structure. The buffer pad 220 is arranged on the outside of the support body 210, and plays an additional support and buffering role for the support body 210. The curved buffer pad 220 can effectively absorb and alleviate the impact force from the outside through its geometric design of the curved surface curvature (60 to 300 mm). Especially when the patient is engaged in daily activities or strenuous exercise, the load on the prosthesis will increase significantly, and the buffer pad 220 can disperse these impact forces through its flexibility and curved surface characteristics to prevent them from being directly transmitted to the bones, thereby improving the stability of the prosthesis and reducing the pain or discomfort caused by the impact force to the patient. The curved surface design of the buffer pad 220 not only performs well in mechanical buffering, but also plays an important protective role in the long-term durability of the prosthesis. During long-term use, the prosthesis often suffers from wear or fatigue due to repeated force. The buffer pad 220 reduces the direct contact between the prosthesis and the bone, reduces the wear rate of the prosthesis material, and extends the service life of the prosthesis by effectively absorbing and dispersing the impact force. In addition, the curvature design of the buffer pad 220 also helps to reduce the friction when the prosthesis contacts the bone tissue, further reducing the damage of the prosthesis to the bone and alleviating the recovery pressure of the patient after surgery. Finally, the coordinated design of the support body 210 and the buffer pad 220 can ensure that the multiple needs of the prosthesis during use are met. The support body 210 provides mechanical support for the prosthesis through its structural strength, while the buffer pad 220 provides additional cushioning and protection for the support body 210 through the geometric structure and material properties of the curved surface. This design enables the prosthesis to protect the patient's bones and soft tissues while coping with external pressure, ensuring that the prosthesis can be in long-term and stable contact with the osteotomy plane. Moreover, this combined design also takes into account the comfort of the patient during postoperative rehabilitation, and reduces the pain or discomfort that the patient may experience when using the prosthesis by reducing local stress and absorbing impact force.The dual design of the support body 210 and the cushion 220 not only improves the biomechanical properties of the prosthesis, but also optimizes the patient's experience. For amputees, the long-term stability and comfort of the prosthesis are crucial, and this design ensures that the prosthesis can maintain stability under high-intensity loads by reasonably distributing external forces and reducing stress concentration. At the same time, the cushioning effect of the cushion 220 greatly reduces the impact of external forces on the prosthesis and bones, improves the durability of the prosthesis and reduces the risk of postoperative complications.

[0041] Specifically, the support column 120 and the supporting body 210 are an integrated structure.

[0042] Specifically, the porous structure layer 110 of the implant and the support column 120 are an integrated structure, and the supporting body 210 and the buffer pad 220 are an integrated structure; the materials of the implant part and the supporting part include but are not limited to titanium alloy, PEEK and other materials.

[0043] It can be seen that through the integrated design and the optimized application of multiple material combinations, the prosthesis has been significantly improved in terms of mechanical properties and biointegration. The integrated design of the support column 120 and the support body 210, the implant porous structure layer 110 and the support column 120, and the support body 210 and the cushion pad 220 eliminates the structural weaknesses in traditional prostheses and ensures the long-term stability and durability of the prosthesis during use. In addition, the application of materials such as titanium alloy and PEEK combines the advantages of strength, durability and biocompatibility, so that the prosthesis can better adapt to the patient's physiological conditions after surgery and provide a more reliable and comfortable rehabilitation experience. This design not only solves the problems of prosthesis loosening, stress concentration and poor biocompatibility, but also provides a solid foundation for the long-term and stable use of the prosthesis, greatly improving the patient's quality of life and rehabilitation effect after surgery.

[0044] It is understandable that the support column 120 and the support body 210, the implant porous structure layer 110 and the support column 120, and the support body 210 and the cushion pad 220 all adopt an integrated design. The core advantage of this design is that it reduces the connection points between the components. In traditional prosthesis design, the connection between multiple components is often the main area of ​​stress concentration and structural weakening. Through the integrated design, these potential weaknesses are eliminated, and the prosthesis can disperse the external force more evenly when subjected to force, ensuring the stability and mechanical strength of the structure. The integrated design of the support column 120 and the support body 210, especially the combination of the implant porous structure layer 110 and the support column 120, not only enhances the overall strength of the prosthesis, but also improves the bio-integration ability of the prosthesis in bone tissue. The integration of the porous structure layer and the support column 120 makes the bio-integration process of the prosthesis more compact and efficient. The porous structure provides an ideal environment for the growth of bone cells, promotes the growth of bone tissue into the prosthesis, and forms a strong bone-prosthesis connection. This close biological integration makes the prosthesis more stable in long-term use, effectively reduces the risk of loosening or falling off of the prosthesis, and the stability of the prosthesis is further guaranteed, especially when subjected to high-intensity loads. In addition, the integrated design of the support body 210 and the buffer pad 220 greatly optimizes the impact relief and pressure dispersion of the prosthesis. The support body 210 provides basic mechanical support through its solid structure, while the buffer pad 220 provides additional buffering function on the outside through the curved surface design. This design can effectively absorb the impact force from the outside, especially when the patient is engaged in strenuous activities, the buffer pad 220 can reduce the direct friction and pressure concentration between the prosthesis and the bone. The curvature design of the curved surface buffer pad 220 can help disperse the force transmission path, ensure that the external force is evenly distributed over a large area, reduce the burden on the osteotomy end, and thus improve the comfort and durability of the prosthesis. The material selection of the prosthesis is also an important part of the technical principle, mainly including materials such as titanium alloy and PEEK. Titanium alloy, as one of the main materials of the prosthesis, has extremely high mechanical strength and excellent corrosion resistance, which enables it to withstand long-term load without deformation or breakage. The high elastic modulus of titanium alloy makes the prosthesis have high rigidity when in use. At the same time, its good biocompatibility prevents it from causing serious rejection reactions after being implanted in the human body, and it can form a stable mechanical connection with bone tissue. Compared with titanium alloy, although the elastic modulus of PEEK material (polyetheretherketone) is lower, its elastic modulus is close to that of bone tissue, which can effectively reduce the stress shielding effect. This means that the prosthesis can transmit force more naturally under load, reduce the stress concentration problem of bone tissue, and promote the normal physiological function of bones. In addition, PEEK has good wear resistance and corrosion resistance, and can maintain its structural integrity during the long-term use of the prosthesis, reducing the degradation of prosthesis performance caused by wear or chemical erosion. The lightweight characteristics of PEEK also help to reduce the overall weight of the prosthesis and improve the wearing comfort of patients.

[0045] Those skilled in the art will appreciate that the embodiments of the present application may be provided as methods, systems or computer program products. Therefore, the present application may adopt the form of a complete hardware embodiment, a complete software embodiment, or an embodiment in combination with software and hardware. Moreover, the present application may adopt the form of a computer program product implemented on one or more computer-usable storage media (including but not limited to disk storage, CD-ROM, optical storage, etc.) containing computer-usable program codes.

[0046] The present application is described with reference to flowcharts and / or block diagrams of methods, devices (systems) and computer program products according to embodiments of the present application. It should be understood that each process and / or box in the flowchart and / or block diagram, as well as the combination of processes and / or boxes in the flowchart and / or block diagram, can be implemented by computer program instructions. These computer program instructions can be provided to a processor of a general-purpose computer, a special-purpose computer, an embedded processor or other programmable data processing device to generate a machine, so that the instructions executed by the processor of the computer or other programmable data processing device generate instructions for implementing the processes in the flowchart and / or block diagram. Figure 1 A process or multiple processes and / or boxes Figure 1 A device that provides the functions specified in a block or multiple blocks.

[0047] These computer program instructions may also be stored in a computer-readable memory capable of directing a computer or other programmable data processing device to operate in a specific manner, so that the instructions stored in the computer-readable memory produce an article of manufacture comprising an instruction device, which implements the process Figure 1 A process or multiple processes and / or boxes Figure 1 A function specified in one or more boxes.

[0048] These computer program instructions can also be loaded onto a computer or other programmable data processing device so that a series of operating steps are executed on the computer or other programmable device to produce a computer-implemented process, thereby providing instructions for implementing the process. Figure 1 A process or multiple processes and / or boxes Figure 1 A step that specifies a function in one or more boxes.

[0049] Finally, it should be noted that the above embodiments are only used to illustrate the technical solutions of the present invention rather than to limit it. Although the present invention has been described in detail with reference to the above embodiments, ordinary technicians in the relevant field should understand that the specific implementation methods of the present invention can still be modified or replaced by equivalents. Any modification or equivalent replacement that does not depart from the spirit and scope of the present invention should be covered within the scope of protection of the claims of the present invention.

Claims

1. A osteotomy repair prosthesis for amputation surgery, characterized in that: include: The prosthesis implant part is arranged inside the connecting bone above the osteotomy plane at the amputation site of the patient; A prosthesis supporting part is arranged at an end of the prosthesis implanting part away from the connecting bone, one end of the prosthesis supporting part is fixedly connected to the prosthesis implanting part and contacts with the bone osteotomy plane; Wherein, the outer surface structure of the prosthesis implant part is a porous structure, which contacts the surface of the bone marrow cavity of the remaining part of the amputated bone.

2. The osteotomy repair prosthesis for amputation surgery according to claim 1, characterized in that: The prosthesis implant part comprises: An implant porous structure layer is arranged inside the connecting bone, the implant porous structure layer is connected to the surface of the bone marrow cavity of the connecting bone, wherein the outer wall of the implant porous structure layer is provided with the porous structure; A support column is arranged inside the porous structure layer of the implant, the support column is connected to the porous structure layer of the implant, and the support column is used to support the porous structure layer of the implant.

3. The osteotomy repair prosthesis for amputation surgery according to claim 2, characterized in that: The end of the implant porous structure layer implanted into the connecting bone is a hemispherical structure.

4. The osteotomy repair prosthesis for amputation surgery according to claim 2, characterized in that: The prosthesis supporting part comprises: A supporting body is arranged at one end of the implant part near the osteotomy plane, the supporting body is respectively connected to the implant part support column and the porous structure layer, and is in contact with the osteotomy end surface; A buffer pad is arranged outside the supporting body, and the buffer pad is used to support the supporting body; Wherein, the buffer pad is a curved structure.

5. The osteotomy repair prosthesis for amputation surgery according to claim 4, characterized in that: The support column and the supporting body are an integrated structure.

6. The osteotomy repair prosthesis for amputation surgery according to claim 2, characterized in that: The porous structure layer of the implant and the support column are an integrated structure, and the support body and the buffer pad are an integrated structure; The materials of the implant porous structure layer, support column, support body and buffer pad include but are not limited to titanium alloy and PEEK material.

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