Unpowered self-adaptive extension backbone prosthesis

Abstract

The invention provides an unpowered self-adaptive extension diaphysis prosthesis, and belongs to the technical field of medical apparatuses and instruments. The near-end prosthesis comprises a matched structure of an articular surface, a first fixing nail hole, a first bolt through hole and a first square sliding groove, or comprises a universal structure of a broach, a second fixing nail hole, a second bolt through hole and a second square sliding groove, and the first fixing nail hole, the first bolt through hole and the first square sliding groove are all formed in the surface of the near-end prosthesis; the near-end prosthesis and the far-end prosthesis are fixed to the two ends of the bone respectively, an extension rod of the mandrel freely slides in a low-friction sliding pair composed of the leading bush and the collar-free bush, and when the bone grows, the prosthesis assembly fixed to the near-end bone can drive the mandrel to generate axial displacement, so that the near-end prosthesis and the far-end prosthesis are fixed to the two ends of the bone respectively. The whole process completely depends on the biomechanical effect generated by natural growth of bones, and external power intervention or secondary operation intervention is not needed.

Description

Technical Field

[0001] The invention belongs to the technical field of medical devices, and in particular relates to a non-powered adaptive lengthening diaphyseal prosthesis. Background Art

[0002] In orthopedic clinical treatment, lesions or injuries of the backbone, such as bone tumor resection, nonunion of fractures, bone defects, etc., often require the use of backbone prostheses for replacement and repair.

[0003] Traditional prosthesis designs are often difficult to perfectly match the patient's bone anatomy, resulting in poor postoperative recovery and possible prosthesis loosening, displacement, etc. On the other hand, for children or patients whose bones are still growing, existing prostheses cannot automatically adapt to the needs of bone growth, and the number of surgeries is high, which brings great pain and economic burden to patients. The matching is poor: the size parameters and shape of traditional diaphyseal prostheses are relatively fixed, and they have good adaptability for the middle area of ​​the skeleton, but the matching is poor when it comes to the distal or proximal end of the skeleton, resulting in unsatisfactory postoperative results. The extension function cannot be adaptive: existing extension prostheses are mostly driven by a threaded screw structure. After a period of growth, the patient needs surgery to open the incision and adjust the nut to achieve extension or replace the osteotomy segment of different lengths to adjust the length, which brings great pain and economic burden to patients. The long-term effect is unsatisfactory: some adaptive prostheses are not fixed enough, which makes the prosthesis function unable to achieve adaptive extension according to bone growth. Summary of the Invention

[0004] The purpose of the present invention is to provide a non-powered adaptive diaphyseal extension prosthesis, which aims to solve the problem that traditional prosthesis designs in the existing technology are often difficult to perfectly match the patient's bone anatomy, resulting in poor postoperative recovery and possible prosthesis loosening, displacement, etc.; on the other hand, for children or patients whose bones are still growing, the existing prosthesis cannot automatically adapt to the needs of bone growth, and the number of surgeries is large, which brings great pain and economic burden to patients.

[0005] To achieve the above object, the present invention provides the following technical solutions: A non-powered adaptive lengthening diaphyseal prosthesis comprising: The proximal prosthesis includes a matching structure comprising an articular surface, a first fixing nail hole, a first bolt through hole, and a first square chute, or a universal structure comprising a medullary pin, a second fixing nail hole, a second bolt through hole, and a second square chute, wherein the first fixing nail hole, the first bolt through hole, and the first square chute are all provided on the surface of the proximal prosthesis; A distal prosthesis comprising a matching structure comprising a first cylindrical hole, a first sleeve, a first distal medullary pin, a matching wing plate, and a first fixing hole, or a universal structure comprising a second cylindrical hole, a second sleeve, a second distal medullary pin, and a second fixing hole, wherein the first cylindrical hole is formed in the distal prosthesis, the first sleeve is located on the surface of the distal prosthesis, and the first distal medullary pin, the matching wing plate, and the first fixing hole are all located on the surface of the distal prosthesis; The core shaft includes a square slide rod, a bolt hole, an osteotomy segment and an extension rod, wherein the square slide rod cooperates with the first square slide groove or the second square slide groove of the proximal prosthesis, the extension rod is slidably connected to the distal prosthesis, the extension rod is fixedly connected to one side end of the square slide rod, the osteotomy segment is fixedly connected to the surface of the square slide rod and the extension rod, and the bolt hole is opened on the surface of the square slide rod; A bushing assembly includes a collared bushing and a collarless bushing, wherein the collared bushing includes a bushing collar, a first bushing and a first axial hole, and the collarless bushing includes a second bushing and a second axial hole, which are sequentially embedded in the first sleeve or the second sleeve of the distal prosthesis; A fixing assembly, comprising a fixing bolt and a screw, wherein the fixing bolt comprises a coarse stud, a thread, a fine stud and a hexagonal hole, and is used to fix the core shaft and the proximal prosthesis; The proximal prosthesis is fixedly connected to one side of the ulna, and the extension rod of the core shaft slides in the bushing assembly to achieve unpowered adaptive extension.

[0006] As a preferred solution of the present invention, in the matching structure of the proximal prosthesis, the articular surface forms an articulated connection with the remaining portion of the distal prosthesis, and the first fixing nail hole is used to fix the proximal prosthesis to the ulna; In the universal structure of the proximal prosthesis, the medullary pin is embedded in the medullary cavity of the bone, and the second fixing nail hole is used to fix the proximal prosthesis and the bone.

[0007] As a preferred solution of the present invention, in the matching structure of the distal prosthesis, the matching wing plate is matched and fixed with the remaining distal portion of the bone; In the universal structure of the distal prosthesis, the second distal medullary pin is embedded in the medullary cavity of the bone, and the second fixing hole is used to fix the distal prosthesis and the bone.

[0008] As a preferred solution of the present invention, the collar of the collared bushing is clamped at the port of the first sleeve or the second sleeve to form a sliding joint surface with the collarless bushing, allowing the extension rod to slide axially and rotate circumferentially.

[0009] As a preferred solution of the present invention, the thick stud of the fixing bolt is adapted to the tightening tool through the hexagonal hole, and the thin stud passes through the first bolt through hole or the second bolt through hole, and the thread locks the core shaft and the proximal prosthesis.

[0010] As a preferred solution of the present invention, the bone contact surfaces of the proximal prosthesis and the distal prosthesis are designed with a porous structure to promote bone ingrowth and achieve long-term stable fixation.

[0011] As a preferred solution of the present invention, the osteotomy segment and extension rod of the core shaft have various specifications and can be individually selected and replaced according to the needs of bone growth.

[0012] As a preferred solution of the present invention, the proximal prosthesis and the distal prosthesis of the prosthesis are respectively fixed to the two ends of the bone. As the bone grows, the extension rod of the core shaft automatically slides in the bushing assembly to achieve unpowered adaptive extension.

[0013] As a preferred solution of the present invention, the components of the prosthesis adopt a modular design, and matching or universal components can be selected for combination use according to the specific conditions of the patient.

[0014] As a preferred solution of the present invention, the prosthesis is manufactured based on digital modeling and 3D printing technology of patient CT data to achieve personalized customization.

[0015] Compared with the prior art, the present invention has the following beneficial effects: 1. The proximal and distal prostheses are fixed to the bone at either end. The extension rod of the mandrel slides freely in a low-friction sliding pair composed of a collared bushing and a collarless bushing. As the bone grows, the prosthetic component fixed to the proximal bone drives the mandrel to produce axial displacement. The entire process relies entirely on the biomechanical effects of natural bone growth, without the need for external force intervention or secondary surgical intervention. This unique mechanical structure design not only solves the clinical pain point of traditional extension prostheses requiring multiple surgical adjustments, but also ensures that the sliding resistance is controlled within the physiologically acceptable range, ensuring that the extension process proceeds synchronously with bone growth.

[0016] 2. The prosthesis achieves unprecedented clinical adaptability through its dual-mode design of matching and universal fit. For patients with unique anatomical morphologies, a personalized matching structure with articular surfaces and matching wing plates can be selected. Using 3D printing technology, the prosthesis achieves millimeter-level matching between the prosthesis and the skeletal anatomy. This flexible configuration enables the prosthesis to address the full spectrum of clinical needs, from children to adults, and from simple cases to complex deformities.

[0017] 3. The prosthesis's biointegration performance significantly outperforms traditional products. The bone-contacting surfaces of the proximal and distal prostheses utilize a specially treated porous structure. This interconnected pore network not only provides an ideal three-dimensional space for bone cell ingrowth, but also features a bioactive surface treatment that accelerates bone integration. The polyethylene articulating surface design, formed by both collared and collarless bushings, ensures sliding function while minimizing the generation of wear particles. BRIEF DESCRIPTION OF THE DRAWINGS

[0018] The accompanying drawings are used to provide a further understanding of the present invention and constitute a part of the specification. Together with the embodiments of the present invention, they are used to explain the present invention and do not constitute a limitation of the present invention. In the accompanying drawings: Figure 1 It is a main perspective view of the present invention; Figure 2 This is the general assembly drawing of the prosthesis of the present invention; Figure 3 Schematic diagram of the matching proximal prosthesis of the present invention; Figure 4 Schematic diagram of the universal proximal prosthesis of the present invention; Figure 5 For the present invention Figure 2 Schematic diagram of the core shaft structure; Figure 6 For the present invention Figure 2 Schematic diagram of the bolt structure; Figure 7 Schematic diagram of the matching distal prosthesis in the present invention; Figure 8 Schematic diagram of the universal distal prosthesis of the present invention; Figure 9 Schematic diagram of the bushing structure in the present invention.

[0019] In the figure: 1. proximal prosthesis; 101. articular surface; 102. first fixing nail hole; 103. first bolt through hole; 104. first square slide; 105. medullary pin; 106. second fixing nail hole; 107. second bolt through hole; 108. second square slide; 2. fixing bolt; 201. thick stud; 202. thread; 203. thin stud; 204. hexagonal hole; 3. mandrel; 301. square slide; 302. bolt hole; 303. osteotomy segment; 304. Extension rod; 4. Collared bushing; 401. Bushing collar; 402. First bushing; 403. First axial hole; 5. Collarless bushing; 501. Second bushing; 502. Second axial hole; 6. Distal prosthesis; 601. First cylindrical hole; 602. First sleeve; 603. First distal medullary needle; 604. Matching wing plate; 605. First fixing hole; 606. Second cylindrical hole; 607. Second sleeve; 608. Second distal medullary needle; 609. Second fixing hole; 7. Bone. DETAILED DESCRIPTION

[0020] The following will clearly and completely describe the technical solutions in the embodiments of the present invention in conjunction with the accompanying drawings. Obviously, the described embodiments are only part of the embodiments of the present invention, not all of the embodiments. Based on the embodiments of the present invention, all other embodiments obtained by ordinary technicians in this field without making creative efforts are within the scope of protection of the present invention.

[0021] Example 1

[0022] See also Figures 1-9 , the present invention provides the following technical solutions: A non-powered adaptive lengthening diaphyseal prosthesis, characterized by comprising: The proximal prosthesis 1 includes a matching structure of an articular surface 101, a first fixing nail hole 102, a first bolt through hole 103, and a first square groove 104, or a universal structure including a medullary pin 105, a second fixing nail hole 106, a second bolt through hole 107, and a second square groove 108. The first fixing nail hole 102, the first bolt through hole 103, and the first square groove 104 are all provided on the surface of the proximal prosthesis 1; The distal prosthesis 6 includes a matching structure comprising a first cylindrical hole 601, a first sleeve 602, a first distal medullary pin 603, a matching wing plate 604, and a first fixing hole 605, or a universal structure comprising a second cylindrical hole 606, a second sleeve 607, a second distal medullary pin 608, and a second fixing hole 609, wherein the first cylindrical hole 601 is formed in the distal prosthesis 6, the first sleeve 602 is located on the surface of the distal prosthesis 6, and the first distal medullary pin 603, the matching wing plate 604, and the first fixing hole 605 are all located on the surface of the distal prosthesis 6; The core shaft 3 includes a square slide bar 301, a bolt hole 302, an osteotomy section 303, and an extension bar 304. The square slide bar 301 cooperates with the first square slide groove 104 or the second square slide groove 108 of the proximal prosthesis 1. The extension bar 304 is slidably connected to the distal prosthesis 6. The extension bar 304 is fixedly connected to one side end of the square slide bar 301. The osteotomy section 303 is fixedly connected to the surfaces of the square slide bar 301 and the extension bar 304. The bolt hole 302 is provided on the surface of the square slide bar 301. The bushing assembly includes a collared bushing 4 and a collarless bushing 5. The collared bushing 4 includes a bushing collar 401, a first bushing 402, and a first axial hole 403. The collarless bushing 5 includes a second bushing 501 and a second axial hole 502. The two are sequentially embedded in the first sleeve 602 or the second sleeve 607 of the distal prosthesis 6. A fixing assembly, including a fixing bolt 2 and a screw, wherein the fixing bolt 2 includes a thick stud 201, a thread 202, a thin stud 203 and a hexagonal hole 204, and is used to fix the core shaft 3 and the proximal prosthesis 1; The proximal prosthesis 1 is fixedly connected to one side of the ulna, and the extension rod 304 of the core shaft 3 slides in the bushing assembly to achieve unpowered adaptive extension.

[0023] In a specific embodiment of the present invention, the device is made of medical titanium alloy + combined polyethylene material. The doctor selects a matching proximal prosthesis 1 according to the patient's bone condition, docks the proximal prosthesis 1 with the articular surface 101 with the patient's bone stump, and forms an articular connection between the articular surface 101 and the distal end of the humerus. When the proximal prosthesis 1 needs to be fixed, a fixing nail is implanted through the first fixing nail hole 102 to firmly connect the prosthesis to the ulna. When the doctor selects a universal proximal prosthesis 1, the medullary needle 105 is inserted into the medullary cavity of the bone 7, and the fixing nail is implanted through the second fixing nail hole 106 to achieve preliminary fixation. When the core shaft 3 needs to be connected, the square slide rod 301 is inserted into the second square slide groove 108, and the bolt hole 302 is aligned with the second bolt through hole 107. The thin stud 203 of the fixing bolt 2 passes through the through hole and is locked with the thread 202 to complete the fixed connection between the core shaft 3 and the proximal prosthesis 1. When installing the distal prosthesis 6, if a matching structure is selected, the matching wing plate 604 is fitted with the distal end of the bone 7, and a screw is implanted through the first fixing hole 605 to fix it. When the bushing assembly needs to be assembled, first put the collarless bushing 5 into the bottom of the first sleeve 602, and then install the collared bushing 4 until it is fixed. When the bushing collar 401 is stuck in the sleeve port, a complete sliding joint surface is formed, which provides a sliding channel for the extension rod 304 of the core shaft 3. When the prosthesis is assembled as a whole, the extension rod 304 of the core shaft 3 connected to the proximal prosthesis 1 is inserted into the first axial hole 403 and the second axial hole 502 of the bushing assembly. When the radius and ulna grow, the proximal prosthesis 1 moves with the bones, driving the extension rod 304 of the core shaft 3 to slide axially in the bushing assembly, realizing the non-powered adaptive extension of the prosthesis length, without the need for secondary surgical intervention. When the prosthesis length needs to be adjusted, it can be replaced according to the patient's growth. The core shaft 3 of the same specification can be quickly replaced by loosening the fixing bolt 2. After the replacement is completed, the fixing bolt 2 is re-tightened to ensure the stability of the prosthesis, meet the personalized needs of different growth stages, and improve the long-term applicability of the prosthesis. The flexible choice of matching and universal designs can meet the anatomical needs of different patients. The bushing component design ensures the smooth sliding and rotation of the extension rod 304. The modular structure facilitates intraoperative adjustment and postoperative maintenance. The non-powered adaptive extension mechanism effectively avoids the pain of multiple surgeries. The porous contact surface promotes bone ingrowth and improves the long-term stability of the prosthesis.

[0024] For details, please refer to Figures 1-9 In the matching structure of the proximal prosthesis 1, the articular surface 101 forms an articulated connection with the remaining portion of the distal end of the humerus, and the first fixing nail hole 102 is used to fix the proximal prosthesis 1 and the ulna; In the universal structure of the proximal prosthesis 1 , the medullary pin 105 is embedded in the medullary cavity of the bone 7 , and the second fixing nail hole 106 is used to fix the proximal prosthesis 1 and the bone 7 .

[0025] In this embodiment: in the matching structure of the proximal prosthesis 1, the joint surface 101 is a polished smooth curved surface, and the first fixing nail hole 102 is conical in design, which facilitates the formation of stable three-point fixation after the bone screw is implanted. In the universal structure of the proximal prosthesis 1, the surface of the medullary pin 105 is provided with a spiral groove to enhance the initial stability with the medullary cavity, and the second fixing nail hole 106 is designed with multi-angle distribution, and the optimal fixation angle can be selected according to the intraoperative situation.

[0026] For details, please refer to Figures 1-9 In the matching structure of the distal prosthesis 6, the matching wing plate 604 is matched and fixed with the remaining distal portion of the bone 7; In the universal structure of the distal prosthesis 6 , the second distal medullary pin 608 is embedded in the medullary cavity of the bone 7 , and the second fixing hole 609 is used to fix the distal prosthesis 6 and the bone 7 .

[0027] In this embodiment: in the matching structure of the distal prosthesis 6, the contour of the matching wing plate 604 is consistent with the distal anatomical morphology of the bone 7, and its inner side is provided with a serrated texture to enhance the fixation effect. In the universal structure of the distal prosthesis 6, the second distal medullary pin 608 adopts a tapered design, and the second fixing hole 609 is an elliptical design to allow fine-tuning of the fixation position.

[0028] For details, please refer to Figures 1-9 The bushing collar 401 of the collared bushing 4 is clamped in the port of the first sleeve 602 or the second sleeve 607, forming a sliding joint surface with the collarless bushing 5, allowing the extension rod 304 to slide axially and rotate circumferentially.

[0029] In this embodiment: the bushing collar 401 of the leading bushing 4 adopts a specific flange structure, which forms a tight fit with the sleeve. The inner wall of the first bushing 402 is provided with a polyethylene material that reduces friction. The collarless bushing 5 also adopts a polyethylene material, and cooperates with the leading bushing 4 to form a low-friction sliding pair.

[0030] For details, please refer to Figures 1-9 The thick stud 201 of the fixing bolt 2 is adapted to the tightening tool through the hexagonal hole 204 , the thin stud 203 passes through the first bolt through hole 103 or the second bolt through hole 107 , and the thread 202 locks the core shaft 3 and the proximal prosthesis 1 .

[0031] In this embodiment, the fixing bolt 2 adopts a differentiated design of thick and thin studs, the threaded portion adopts a specific form of thread structure, and the hexagonal hole 204 adopts a specific depth design to ensure sufficient torque transmission capacity. For details, please refer to Figures 1-9 The bone contact surfaces of the proximal prosthesis 1 and the distal prosthesis 6 are designed with a porous structure to promote bone ingrowth and achieve long-term stable fixation.

[0032] In this embodiment, the porous structure has a specific pore size and porosity design that is interconnected, and the surface is specially treated to enhance biological activity. For details, please refer to Figures 1-9 The osteotomy section 303 and the extension rod 304 of the core shaft 3 have various specifications and can be personalized and replaced according to the needs of bone growth.

[0033] In this embodiment, the osteotomy section 303 and the extension rod 304 of the core shaft 3 are provided with a variety of sizes and specifications for selection, and the surface is specially treated to optimize the friction characteristics.

[0034] For details, please refer to Figures 1-9 The proximal prosthesis 1 and the distal prosthesis 6 of the prosthesis are respectively fixed to the two ends of the bone 7. As the bone grows, the extension rod 304 of the core shaft 3 automatically slides in the bushing assembly to achieve unpowered adaptive extension.

[0035] In this embodiment, during the automatic sliding process, the sliding resistance between the extension rod 304 and the bushing assembly is controlled within a specific range, while allowing a certain angle of physiological rotation.

[0036] For details, please refer to Figures 1-9 The components of the prosthesis adopt a modular design, and matching or universal components can be selected for combination according to the patient's specific situation.

[0037] In this embodiment: in the modular design, the connection interfaces of each component adopt a standardized design, and the mating surfaces adopt a specific tolerance matching grade.

[0038] For details, please refer to Figures 1-9 The production of prostheses is based on digital modeling of patient CT data and 3D printing technology to achieve personalized customization.

[0039] In this embodiment: 3D printing adopts specific process parameters, the printing material is medical-grade titanium alloy, and it undergoes a specific post-processing process.

[0040] The working principle and use process of the present invention are as follows: according to the patient's bone anatomical characteristics, a matching or universal proximal prosthesis 1 and a distal prosthesis 6 are selected, and the length specification of the core shaft 3 is determined, and the distal prosthesis 6 is implanted; matching structure: the matching wing plate 604 is accurately aligned with the distal end of the bone, and a screw is implanted through the first fixing hole 605 to fix it; universal structure: the second distal medullary pin 608 is inserted into the medullary cavity and fixed through the second fixing hole 609; bushing assembly installation: the collarless bushing 5 and the collared bushing 4 are sequentially embedded in the first sleeve 602 or the second sleeve 607, ensuring that the bushing collar 401 is stuck in the sleeve port, and the proximal prosthesis 1 is implanted; matching structure: the joint surface 101 is aligned with the bone stump Position, implant the fixing nail through the first fixing nail hole 102, universal structure: insert the medullary needle 105 into the medullary cavity, fix it through the second fixing nail hole 106, and connect the core shaft 3; insert the square slide rod 301 into the first square slide groove 104 or the second square slide groove 108 of the proximal prosthesis 1, pass the thin stud 203 of the fixing bolt 2 through the bolt hole 302, lock it with the thread 202, fix the core shaft 3 and the proximal prosthesis 1, insert the extension rod 304 into the first axial hole 403 or the second axial hole 502 of the bushing assembly, check the sliding and rotation functions of the prosthesis, ensure that the extension rod 304 slides smoothly in the bushing assembly, and confirm that the proximal prosthesis 1 and the distal prosthesis 6 are firmly fixed without looseness.

[0041] Finally, it should be noted that the above descriptions are merely preferred embodiments of the present invention and are not intended to limit the present invention. Although the present invention has been described in detail with reference to the aforementioned embodiments, those skilled in the art will be able to modify the technical solutions described in the aforementioned embodiments or substitute equivalents for some of the technical features. Any modifications, equivalent substitutions, and improvements made within the spirit and principles of the present invention shall be included within the scope of protection of the present invention.

Claims

1. A non-powered adaptive lengthening diaphyseal prosthesis, characterized by: include: A proximal prosthesis (1) comprising a matching structure of a joint surface (101), a first fixing nail hole (102), a first bolt through hole (103) and a first square slide groove (104), or a universal structure comprising a medullary pin (105), a second fixing nail hole (106), a second bolt through hole (107) and a second square slide groove (108), wherein the first fixing nail hole (102), the first bolt through hole (103) and the first square slide groove (104) are all provided on the surface of the proximal prosthesis (1); A distal prosthesis (6) comprising a matching structure of a first cylindrical hole (601), a first sleeve (602), a first distal medullary needle (603), a matching wing plate (604) and a first fixing hole (605), or a universal structure comprising a second cylindrical hole (606), a second sleeve (607), a second distal medullary needle (608) and a second fixing hole (609), wherein the first cylindrical hole (601) is opened in the distal prosthesis (6), the first sleeve (602) is located on the surface of the distal prosthesis (6), and the first distal medullary needle (603), the matching wing plate (604) and the first fixing hole (605) are all located on the surface of the distal prosthesis (6); A core shaft (3) includes a square slide bar (301), a bolt hole (302), an osteotomy section (303) and an extension rod (304), wherein the square slide bar (301) cooperates with the first square slide groove (104) or the second square slide groove (108) of the proximal prosthesis (1), the extension rod (304) is slidably connected to the distal prosthesis (6), the extension rod (304) is fixedly connected to one side end of the square slide bar (301), the osteotomy section (303) is fixedly connected to the surfaces of the square slide bar (301) and the extension rod (304), and the bolt hole (302) is opened on the surface of the square slide bar (301); A bushing assembly comprises a collared bushing (4) and a collarless bushing (5), wherein the collared bushing (4) comprises a bushing collar (401), a first bushing (402) and a first axial hole (403), and the collarless bushing (5) comprises a second bushing (501) and a second axial hole (502), which are sequentially embedded in the first sleeve (602) or the second sleeve (607) of the distal prosthesis (6); A fixing assembly, comprising a fixing bolt (2) and a screw, wherein the fixing bolt (2) comprises a thick stud (201), a thread (202), a thin stud (203) and a hexagonal hole (204), and is used to fix the core shaft (3) and the proximal prosthesis (1); The proximal prosthesis (1) is fixedly connected to one side of the ulna, and the extension rod (304) of the core shaft (3) slides in the bushing assembly to achieve unpowered adaptive extension.

2. The non-powered adaptive lengthening diaphyseal prosthesis according to claim 1, characterized in that: In the matching structure of the proximal prosthesis (1), the articular surface (101) forms an articulated connection with the remaining portion of the distal end of the humerus, and the first fixing nail hole (102) is used to fix the proximal prosthesis (1) and the proximal end of the ulna; In the universal structure of the proximal prosthesis (1), the medullary needle (105) is embedded in the medullary cavity of the bone (7), and the second fixing nail hole (106) is used to fix the proximal prosthesis (1) and the bone (7).

3. The non-powered adaptive lengthening diaphyseal prosthesis according to claim 2, characterized in that: In the matching structure of the distal prosthesis (6), the matching wing plate (604) is matched and fixed with the distal remaining portion of the bone (7); In the universal structure of the distal prosthesis (6), the second distal medullary needle (608) is embedded in the medullary cavity of the bone (7), and the second fixing hole (609) is used to fix the distal prosthesis (6) and the bone (7).

4. The non-powered adaptive lengthening diaphyseal prosthesis according to claim 3, characterized in that: The bushing collar (401) of the collared bushing (4) is clamped at the port of the first sleeve (602) or the second sleeve (607), forming a sliding joint surface with the collarless bushing (5), allowing the extension rod (304) to slide axially and rotate circumferentially.

5. The non-powered adaptive lengthening diaphyseal prosthesis according to claim 4, characterized in that: The thick stud (201) of the fixing bolt (2) is adapted to the tightening tool through the hexagonal hole (204), the thin stud (203) passes through the first bolt through hole (103) or the second bolt through hole (107), and the thread (202) locks the core shaft (3) and the proximal prosthesis (1).

6. The non-powered adaptive lengthening diaphyseal prosthesis according to claim 5, characterized in that: The bone contact surfaces of the proximal prosthesis (1) and the distal prosthesis (6) are designed with a porous structure to promote bone ingrowth and achieve long-term stable fixation.

7. The non-powered adaptive lengthening diaphyseal prosthesis according to claim 6, characterized in that: The osteotomy section (303) and the extension rod (304) of the core shaft (3) have various specifications and can be individually selected and replaced according to bone growth requirements.

8. The non-powered adaptive lengthening diaphyseal prosthesis according to claim 7, characterized in that: The proximal prosthesis (1) and the distal prosthesis (6) of the prosthesis are respectively fixed to the two ends of the bone (7); as the bone grows, the extension rod (304) of the core shaft (3) automatically slides in the bushing assembly, achieving unpowered adaptive extension.

9. The non-powered adaptive lengthening diaphyseal prosthesis according to claim 8, characterized in that: The components of the prosthesis adopt a modular design, and matching or universal components can be selected for combination use according to the patient's specific conditions.

10. The non-powered adaptive lengthening diaphyseal prosthesis according to claim 9, characterized in that: The prosthesis is manufactured based on digital modeling of patient CT data and 3D printing technology to achieve personalized customization.

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