Transverse tibia moving device

Abstract

The invention relates to the technical field of medical instruments, and discloses a tibia transverse moving device which comprises a traction mechanism, two connecting rod mechanisms connected to the two sides of the traction mechanism, a universal rotating mechanism arranged at the tail ends of the connecting rod mechanisms and a long bone needle clamping mechanism arranged at the tail end of the universal rotating mechanism. Wherein the traction mechanism is configured to drive a bone block to move transversely, the connecting rod mechanism comprises a length-adjustable telescopic unit, and the universal rotating mechanism realizes three-dimensional angle adjustment. Through the synergistic effect of all the components, the surgical suitability and the operation accuracy can be effectively improved.

Description

Technical Field

[0001] This invention relates to the field of medical device technology, specifically to a tibial transverse transport device. Background Technology

[0002] Tibial transverse bone transport is an important technique for treating lower limb ischemic diseases (such as diabetic foot and thromboangiitis obliterans). Its core lies in stimulating local angiogenesis and microcirculation reconstruction through slow, precise transverse displacement of bone fragments, thereby improving blood supply to the lower limbs. The clinical efficacy of this technique highly depends on the structural rationality and operational precision of the bone transport device. Whether the device can adapt to individual anatomical differences in patients, achieve stable fixation of the bone pin, and allow for dynamic adjustment directly affects surgical safety and treatment prognosis.

[0003] Currently, clinically used tibial transverse transport devices have significant technical limitations and cannot meet the needs of complex surgeries, mainly in the following aspects:

[0004] The lack of adjustable linkage length and insufficient adaptability are significant drawbacks: Existing devices often employ rigid, fixed linkage mechanisms, whose length cannot be dynamically adjusted based on the patient's tibial anatomy (such as tibial length, diameter, and bone fragment size). During surgery, insufficient compatibility between the device and the patient's bone structure frequently leads to misalignment of the bone pin implantation and unstable device fixation. This not only increases the difficulty of the procedure but may also cause additional bone damage due to the rigid contact between the device and the bone surface.

[0005] Limited adjustment of bone pin angle and poor fixation stability: Traditional bone pin clamping mechanisms lack omnidirectional rotation, limiting their angle adjustment range to small angles within a single plane. When encountering patients with irregular tibial morphology (e.g., deformities, bone hyperplasia) or when surgery requires non-standard angle implantation of bone pins (e.g., adjusting the implantation direction to avoid important blood vessels and nerves), the bone pin cannot achieve the optimal fit angle with the bone surface, resulting in poor fixation. This instability can lead to stress concentration during surgery, causing microfractures or resorption of the bone around the pin. Furthermore, during postoperative bone fragment movement, bone fragment displacement and rotation are prone to occur, directly affecting the treatment goals of angiogenesis and microcirculation reconstruction, and increasing the risk of postoperative complications (e.g., nonunion, infection).

[0006] Therefore, in order to address the shortcomings of existing tibial transverse transport devices in terms of adaptability and angle adjustment, developing a new device with telescopic adjustment and omnidirectional rotation capabilities to improve the clinical applicability and surgical precision has become an urgent technical problem to be solved in this field. Summary of the Invention

[0007] In view of this, the present invention provides a tibial transverse transport device to solve the above-mentioned problems.

[0008] This invention provides a tibial transverse transport device, comprising:

[0009] Traction mechanism;

[0010] Two linkage mechanisms connected to both sides of the traction mechanism;

[0011] A universal rotating mechanism is provided at the end of the linkage mechanism;

[0012] Long bone needle clamping mechanism is provided at the end of the universal rotating mechanism;

[0013] The traction mechanism is configured to drive the lateral displacement of the bone block, the linkage mechanism includes a telescopic unit with adjustable length, and the universal rotation mechanism realizes three-dimensional angle adjustment.

[0014] This tibial transverse transport device effectively improves surgical adaptability and operational precision through the synergistic effect of its components. The traction mechanism stably drives the lateral displacement of the bone fragment, ensuring that the fragment moves along the expected path and creating favorable conditions for angiogenesis and microcirculation reconstruction. The telescopic unit of the linkage mechanism can flexibly adjust its length to adapt to the anatomical differences of the tibia in different patients, avoiding instability caused by mismatch between the device and the bone structure. The three-dimensional angle adjustment function of the universal rotation mechanism can meet the non-standard angle implantation needs of bone pins in complex surgical scenarios, enhance the fixation effect of bone pins, reduce intraoperative stress concentration damage to the bone tissue around the bone pins, and reduce the risk of postoperative complications such as bone fragment displacement, thereby improving the overall treatment effect.

[0015] In one optional embodiment, the long bone needle clamping mechanism includes:

[0016] Omnidirectional cue;

[0017] A pair of semi-circular clamps connected by a hinge axis;

[0018] The universal ball joint is fixed to a semi-circular clamp on one side, and the long bone needle is fixed to the semi-circular clamp on the other side by a locking device.

[0019] The long bone pin clamping mechanism, through the cooperation of a universal ball joint and a pair of semi-circular clamps, achieves stable clamping and flexible angle adaptation of the long bone pin. The universal ball joint can rotate flexibly with the adjustment of the universal rotation mechanism, driving the semi-circular clamps fixed to it to adjust their angle. This allows the pair of semi-circular clamps to adapt to the long bone pin implantation needs at different angles, ensuring a close fit between the long bone pin and the bone. At the same time, the pair of semi-circular clamps connected by a hinge shaft, under the action of the locking device, can firmly fix the long bone pin, preventing it from loosening or shifting during surgery, reducing bone damage caused by unstable fixation of the long bone pin, and improving the safety and precision of the surgery.

[0020] In one alternative embodiment, the linkage mechanism includes:

[0021] Hollow connecting rod;

[0022] A solid connecting rod nested within a hollow connecting rod;

[0023] Link fasteners installed at the ends of hollow link rods;

[0024] The connecting rod fastener controls the extension, retraction, and locking of the solid connecting rod via a threaded connection.

[0025] The linkage mechanism, through a combination of hollow and solid links and link fasteners, achieves flexible length adjustment and stable locking, significantly improving the device's adaptability to the anatomical differences of the tibia in different patients. The nested structure of the hollow and solid links allows for free adjustment of the overall length according to the patient's tibial length, bone size, and other actual conditions, avoiding the device-bone mismatch problem caused by the fixed length of traditional rigid links. The locking function of the link fasteners, achieved through threaded connections, firmly fixes the solid and hollow links after the length adjustment, ensuring that the link length remains stable during surgery. This prevents bone displacement caused by link loosening and ensures that the bone moves precisely along the preset path, providing a stable mechanical environment for angiogenesis and microcirculation reconstruction.

[0026] In one optional implementation, the omnidirectional rotation mechanism includes:

[0027] shell;

[0028] A clamping plate is disposed within the outer casing;

[0029] A clamping screw that engages with the threaded clamping plate;

[0030] A rotary wrench that drives the clamping screw;

[0031] The clamping plate contacts the spherical surface of the universal joint rod, and the universal angle is locked by tightening the clamping screw.

[0032] The omnidirectional rotating mechanism, through the coordinated action of the outer shell, clamping plate, clamping screw, and rotating wrench, enables flexible multi-angle adjustment and stable locking of the omnidirectional ball joint, significantly improving the device's adaptability to complex bone morphologies and surgical paths. The spherical contact design between the clamping plate and the omnidirectional ball joint allows the ball joint to rotate freely in three-dimensional space, meeting the needs of non-standard angle implantation of bone pins. The rotating wrench drives the clamping screw, which, through threaded engagement, pushes the clamping plate tightly against the spherical surface of the omnidirectional ball joint, precisely locking the adjusted angle. This avoids unstable bone pin fixation or stress concentration caused by angle deviation during surgery, reducing the risk of bone damage, ensuring the stability of bone fragment transport, and contributing to the achievement of treatment goals such as vascular regeneration and microcirculation reconstruction.

[0033] In one alternative embodiment, the traction mechanism includes:

[0034] Fixed block;

[0035] The rising bolt that penetrates the fixing block;

[0036] An adjusting block fitted onto the rising bolt;

[0037] An adjustment knob that drives the adjustment block to rise and fall;

[0038] Short bone needles fixed on both sides of the adjustment block.

[0039] The traction mechanism, through the coordinated design of a fixed block, rising bolt, adjusting block, adjusting knob, and short bone pins, enables precise lateral traction of bone fragments, providing stable power output and reliable fixation support for tibial lateral transport surgery. The fixed block, as the core load-bearing component, provides the structural foundation for the entire traction mechanism. The cooperation between the rising bolt and the adjusting block allows the adjusting knob to drive the adjusting block up and down, thereby driving the short bone pins to achieve controllable traction of the bone fragments. This ensures the bone fragments move precisely along a preset path, creating favorable conditions for angiogenesis and microcirculation reconstruction. The short bone pins, fixed to both sides of the adjusting block, firmly anchor the bone, preventing slippage or displacement during traction, ensuring stable transmission of traction force, reducing the risk of bone damage due to operational errors, and improving the controllability of surgical outcomes.

[0040] In one optional embodiment, the adjusting block is provided with:

[0041] The bone pin adjustment knob screw is used to lock the rotation position of the adjustment knob;

[0042] The short bone pin screw is used to fix the implantation depth of the short bone pin.

[0043] Through the synergistic action of these two screws, the adjusting block can stably maintain its preset position, and the short bone pin can firmly maintain the set implantation depth, providing a reliable guarantee for the precise operation of the traction mechanism. The bone pin adjustment knob screw and the short bone pin fixing screw on the adjusting block further enhance the operational precision and fixation stability of the traction mechanism, providing dual protection for the controllability of the tibial transverse transport process. The bone pin adjustment knob screw can precisely lock the rotation position of the adjustment knob after the adjusting block is driven to the desired position by the adjustment knob, avoiding displacement of the adjusting block due to accidental rotation of the adjustment knob during surgery, ensuring the consistency of the bone block transport path, and reducing interference with angiogenesis caused by positional deviations. The short bone pin fixing screw can firmly lock the implantation depth of the short bone pin, preventing axial slippage of the short bone pin during transport, ensuring the anchoring effect of the short bone pin on the bone, avoiding bone damage caused by unstable transmission of transport force, and improving the overall safety and reliability of the surgery.

[0044] In one optional embodiment, the hollow connecting rod is connected to the traction mechanism via a connecting rod fixing clamp, and the connecting rod fixing clamp is provided with screws for fixing the hollow connecting rod to achieve quick assembly and disassembly.

[0045] In one alternative embodiment, the inner wall of the semi-circular clamp is provided with an elastic buffer layer to disperse the stress of the bone needle clamping.

[0046] In one alternative embodiment, a lubricating coating is provided between the housing and the clamping plate to reduce omnidirectional rotational friction resistance.

[0047] In one alternative embodiment, all rotating adjustment components of the device are provided with anti-slip textures and scale markings. Attached Figure Description

[0048] To more clearly illustrate the specific embodiments of the present invention or the technical solutions in the prior art, the drawings used in the description of the specific embodiments or the prior art will be briefly introduced below. Obviously, the drawings described below are some embodiments of the present invention. For those skilled in the art, other drawings can be obtained from these drawings without creative effort.

[0049] Figure 1 This is an overall structural diagram of a tibial transverse transport device according to an embodiment of the present invention;

[0050] Figure 2 This is a cross-sectional view of the telescopic link of a tibial transverse transport device according to an embodiment of the present invention;

[0051] Figure 3 This is a cross-sectional view of the universal rotation mechanism of a tibial transverse transport device according to an embodiment of the present invention.

[0052] Explanation of reference numerals in the attached figures:

[0053] 1. Long bone needle;

[0054] 2. Long bone needle clamping mechanism; 21. First semi-circular clamp; 22. Second semi-circular clamp; 23. Universal ball joint;

[0055] 3. Universal rotating mechanism; 31. Rotary wrench; 32. Clamping screw; 33. Housing; 34. Clamping plate; 35. Base plate cover;

[0056] 4. Linkage mechanism; 41. Solid link; 42. Linkage fastener; 43. Hollow link;

[0057] 5. Rising bolts;

[0058] 6. Adjusting block;

[0059] 7. Fix the short bone pin screws;

[0060] 8. Fixing block;

[0061] 9. Connecting rod fixing clamp;

[0062] 10. Fix the hollow connecting rod screws;

[0063] 11. Short bone needle;

[0064] 12. Adjust the knob;

[0065] 13. Bone needle adjustment knob screw. Detailed Implementation

[0066] To make the objectives, technical solutions, and advantages of the embodiments of the present invention clearer, the technical solutions of the embodiments of the present invention will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only some embodiments of the present invention, not all embodiments. Based on the embodiments of the present invention, all other embodiments obtained by those skilled in the art without creative effort are within the scope of protection of the present invention.

[0067] Tibial transverse bone transport is an important technique for treating lower limb ischemic diseases (such as diabetic foot and thromboangiitis obliterans). Its core lies in stimulating local angiogenesis and microcirculation reconstruction through slow, precise transverse displacement of bone fragments, thereby improving blood supply to the lower limbs. The clinical efficacy of this technique highly depends on the structural rationality and operational precision of the bone transport device. Whether the device can adapt to individual anatomical differences in patients, achieve stable fixation of the bone pin, and allow for dynamic adjustment directly affects surgical safety and treatment prognosis.

[0068] Currently, clinically used tibial transverse transport devices have significant technical limitations and cannot meet the needs of complex surgeries, mainly in the following aspects:

[0069] The lack of adjustable linkage length and insufficient adaptability are significant drawbacks: Existing devices often employ rigid, fixed linkage mechanisms, whose length cannot be dynamically adjusted based on the patient's tibial anatomy (such as tibial length, diameter, and bone fragment size). During surgery, insufficient compatibility between the device and the patient's bone structure frequently leads to misalignment of the bone pin implantation and unstable device fixation. This not only increases the difficulty of the procedure but may also cause additional bone damage due to the rigid contact between the device and the bone surface.

[0070] Limited adjustment of bone pin angle and poor fixation stability: Traditional bone pin clamping mechanisms lack omnidirectional rotation, limiting their angle adjustment range to small angles within a single plane. When encountering patients with irregular tibial morphology (e.g., deformities, bone hyperplasia) or when surgery requires non-standard angle implantation of bone pins (e.g., adjusting the implantation direction to avoid important blood vessels and nerves), the bone pin cannot achieve the optimal fit angle with the bone surface, resulting in poor fixation. This instability can lead to stress concentration during surgery, causing microfractures or resorption of the bone around the pin. Furthermore, during postoperative bone fragment movement, bone fragment displacement and rotation are prone to occur, directly affecting the treatment goals of angiogenesis and microcirculation reconstruction, and increasing the risk of postoperative complications (e.g., nonunion, infection).

[0071] Therefore, in order to address the shortcomings of existing tibial transverse transport devices in terms of adaptability and angle adjustment, developing a new device with telescopic adjustment and omnidirectional rotation capabilities to improve the clinical applicability and surgical precision has become an urgent technical problem to be solved in this field.

[0072] The following is combined Figures 1 to 3 The following describes embodiments of the present invention.

[0073] According to an embodiment of the present invention, a tibial transverse transport device is provided, including a traction mechanism, two linkage mechanisms 4 connected to both sides of the traction mechanism, a universal rotating mechanism 3 disposed at the end of the linkage mechanism 4, and a long bone pin clamping mechanism 2 disposed at the end of the universal rotating mechanism 3; wherein, the traction mechanism is configured to drive the transverse displacement of the bone block, the linkage mechanism 4 includes a telescopic unit with adjustable length, and the universal rotating mechanism 3 realizes three-dimensional angle adjustment.

[0074] Linkage mechanism 4 connects to both sides of the traction mechanism. Its telescopic unit can be adjusted in length according to the actual condition of the patient's tibia. When adjustment is needed, the telescopic unit changes its length to fit the bone structure, ensuring a reasonable relative position between the device and the patient's bone. Universal rotation mechanism 3 is located at the end of linkage mechanism 4 and can be adjusted in three dimensions. By adjusting the angle, the long bone pin clamping mechanism 2 connected to its end can adapt to different bone pin implantation angle requirements. After the universal rotation mechanism 3 is adjusted into place, the long bone pin clamping mechanism 2 firmly clamps the long bone pin 1, ensuring the stability of the bone pin during surgery. Ultimately, through the cooperation of all parts, precise lateral displacement of the tibia is achieved.

[0075] This tibial transverse transport device effectively improves surgical adaptability and operational precision through the synergistic effect of its components. The traction mechanism stably drives the transverse displacement of the bone fragment, ensuring that the fragment moves along the expected path, creating favorable conditions for angiogenesis and microcirculation reconstruction. The telescopic unit of the linkage mechanism 4 can flexibly adjust its length to adapt to the anatomical differences of the tibia in different patients, avoiding instability caused by mismatch between the device and the bone structure. The three-dimensional angle adjustment function of the universal rotation mechanism 3 can meet the non-standard angle implantation needs of bone pins in complex surgical scenarios, enhance the fixation effect of bone pins, reduce intraoperative stress concentration damage to the bone tissue around the bone pins, reduce the risk of postoperative complications such as bone fragment displacement, and thus improve the overall treatment effect.

[0076] In one embodiment, the long bone needle clamping mechanism 2 includes a universal ball joint 23 and a pair of semi-circular clamps connected by a hinge shaft; the universal ball joint 23 is fixedly connected to the second semi-circular clamp 22, and the first semi-circular clamp 21 on the other side is fixed to the long bone needle 1 by a locking member.

[0077] During operation, the universal ball joint 23 acts as a connecting component, linking the second semi-circular clamp 22 to the universal rotating mechanism 3. It rotates synchronously with the three-dimensional angle adjustment of the universal rotating mechanism 3, thereby adjusting the second semi-circular clamp 22 on that side to a suitable angle. Since the pair of semi-circular clamps are connected by a hinge shaft, they can rotate around the hinge shaft to open or close. When clamping the long bone pin 1, the long bone pin 1 is first placed between the two semi-circular clamps, and then the locking element locks the first semi-circular clamp 21 on the other side, ensuring a tight fit between the two semi-circular clamps and firmly fixing the long bone pin 1. Through this coordination, the long bone pin clamping mechanism 2 can adapt to different angle requirements with the help of the universal ball joint 23, and ensure the stable clamping of the long bone pin 1 through the action of the semi-circular clamps and the locking element, providing reliable bone pin fixation support for tibial transverse transport surgery.

[0078] The long bone pin clamping mechanism 2, through the cooperation of the universal ball joint 23 and a pair of semi-circular clamps, can achieve stable clamping and flexible angle adaptation of the long bone pin 1. The universal ball joint 23 can rotate flexibly with the adjustment of the universal rotation mechanism 3, driving the second semi-circular clamp 22 fixed thereto to adjust its angle, so that the pair of semi-circular clamps can adapt to the implantation needs of the long bone pin 1 at different angles, ensuring that the long bone pin 1 fits tightly with the bone; at the same time, the pair of semi-circular clamps connected by the hinge shaft can firmly fix the long bone pin 1 under the action of the locking element, preventing the long bone pin 1 from loosening or shifting during the operation, reducing bone damage caused by unstable fixation of the long bone pin 1, and improving the safety and precision of the operation.

[0079] In one embodiment, the linkage mechanism 4 includes a hollow link 43, a solid link 41 nested within the hollow link 43, and a link fastener 42 disposed at the end of the hollow link 43; the link fastener 42 controls the extension, retraction, and locking of the solid link 41 through a threaded connection.

[0080] During operation, the hollow connecting rod 43 serves as the basic component, with one end connected to the traction mechanism and the other end engaging with the solid connecting rod 41 via the connecting rod fastener 42. When the length of the connecting rod mechanism 4 needs adjustment, the connecting rod fastener 42 is rotated in the reverse direction to create a gap between it and the solid connecting rod 41. At this time, the solid connecting rod 41 can freely extend and retract within the hollow connecting rod 43 until a suitable length is achieved to fit the patient's bone. Once the length is determined, the connecting rod fastener 42 is rotated in the forward direction, using the locking force of the threaded connection to tightly fix the solid connecting rod 41 and the hollow connecting rod 43, preventing relative movement between them. Through this process, the connecting rod mechanism 4 can flexibly adjust its length to adapt to different surgical needs while ensuring structural stability after fixation, providing reliable support for the overall operation of the tibial transverse transport device.

[0081] The linkage mechanism 4, through the combined design of hollow link 43, solid link 41, and link fastener 42, achieves flexible length adjustment and stable locking, significantly improving the device's adaptability to the anatomical differences of different patients' tibias. The nested structure of hollow link 43 and solid link 41 allows for free adjustment of the overall length according to the patient's tibial length, bone size, and other actual conditions, avoiding the device-bone mismatch problem caused by the fixed length of traditional rigid links. The locking function of the link fastener 42, achieved through threaded connection, firmly fixes the solid link 41 and hollow link 43 after the length adjustment, ensuring that the link length remains stable during surgery, preventing bone displacement caused by link loosening, and ensuring that the bone moves precisely along the preset path, providing a stable mechanical environment for angiogenesis and microcirculation reconstruction.

[0082] In one embodiment, the universal rotation mechanism 3 includes a housing 33, a clamping plate 34 disposed within the housing 33, a clamping screw 32 threadedly engaged with the clamping plate 34, and a rotary wrench 31 for driving the clamping screw 32; the clamping plate 34 contacts the spherical surface of the universal ball joint 23, and the universal angle is locked by tightening the clamping screw 32.

[0083] During operation, the outer casing 33 provides structural support for the entire universal rotating mechanism 3, and internally houses components such as the clamping plate 34 and the clamping screw 32. When the universal angle needs to be adjusted, the rotary wrench 31 is rotated in the reverse direction, causing the clamping screw 32 to rotate in the opposite direction. This loosens the threaded engagement between the clamping screw 32 and the clamping plate 34, creating a gap between the clamping plate 34 and the spherical surface of the universal ball joint 23. At this point, the universal ball joint 23 can rotate freely to adjust to the desired angle. After the angle is determined, the rotary wrench 31 is rotated in the forward direction, driving the clamping screw 32 to rotate in the forward direction. The threaded thrust pushes the clamping plate 34 towards the spherical surface of the universal ball joint 23 until they make close contact. Through friction, the position of the universal ball joint 23 is firmly locked, thus fixing the adjusted angle. Through this process, the universal rotating mechanism 3 can achieve flexible three-dimensional angle adjustment and ensure the stability and reliability of the adjusted angle, providing precise angle support for the long bone pin clamping mechanism 2 and ensuring the smooth progress of tibial transverse transport surgery.

[0084] The omnidirectional rotating mechanism 3, through the coordinated action of the housing 33, clamping plate 34, clamping screw 32, and rotating wrench 31, enables flexible multi-angle adjustment and stable locking of the omnidirectional ball joint 23, significantly improving the device's adaptability to complex bone morphologies and surgical paths. The spherical contact design between the clamping plate 34 and the omnidirectional ball joint 23 allows the omnidirectional ball joint 23 to rotate freely in three-dimensional space, meeting the needs of non-standard angle implantation of bone pins. Furthermore, by using the rotating wrench 31 to drive the clamping screw 32, the threaded engagement pushes the clamping plate 34 to tightly fit the spherical surface of the omnidirectional ball joint 23, thereby precisely locking the adjusted angle. This avoids unstable bone pin fixation or stress concentration caused by angle deviation during surgery, reducing the risk of bone damage, ensuring the stability of bone block transport, and contributing to the achievement of treatment goals such as vascular regeneration and microcirculation reconstruction.

[0085] In one embodiment, the traction mechanism includes a fixed block 8, a rising bolt 5 passing through the fixed block 8, an adjusting block 6 sleeved on the rising bolt 5, an adjusting knob 12 for driving the adjusting block 6 to rise and fall, and short bone needles 11 fixed on both sides of the adjusting block 6.

[0086] During operation, the fixed block 8 provides a mounting base for components such as the rising bolt 5 and the adjusting block 6. The rising bolt 5 passes through the fixed block 8 and is fixed with its threads. When it is necessary to drive the lateral movement of the bone block, rotating the adjusting knob 12, in conjunction with the rising bolt 5, causes the adjusting block 6 to rise and fall along the rising bolt 5. The rise and fall of the adjusting block 6 synchronously drives the short bone pins 11 on both sides to move. Since the short bone pins 11 are anchored to the bone, the traction operation of the bone block is realized. During the adjustment process, the fixed block 8 ensures the stability of the entire mechanism, the rising bolt 5 provides guidance for the movement of the adjusting block 6, the adjusting knob 12 achieves precise control of the rise and fall of the adjusting block 6 through threaded transmission, and the short bone pins 11 convert the movement of the adjusting block 6 into an effective traction force on the bone block. Through the coordinated action of each component, the traction action of lateral movement of the tibia is completed.

[0087] The traction mechanism, through the coordinated design of the fixing block 8, the rising bolt 5, the adjusting block 6, the adjusting knob 12, and the short bone pins 11, enables precise lateral traction of the bone fragments, providing stable power output and reliable fixation support for tibial lateral transport surgery. The fixing block 8, as the core load-bearing component, provides the structural foundation for the entire traction mechanism. The cooperation between the rising bolt 5 and the adjusting block 6 allows the adjusting knob 12 to drive the adjusting block 6 up and down, thereby driving the short bone pins 11 to achieve controllable traction of the bone fragments, ensuring precise movement along a preset path and creating favorable conditions for angiogenesis and microcirculation reconstruction. The short bone pins 11, fixed to both sides of the adjusting block 6, firmly anchor the bone, preventing slippage or displacement during traction, ensuring stable transmission of traction force, reducing the risk of bone damage due to operational errors, and improving the controllability of surgical outcomes.

[0088] In one embodiment, the adjustment block 6 is provided with a bone pin adjustment knob screw 13 for locking the rotation position of the adjustment knob 12; and a short bone pin fixing screw 7 for fixing the implantation depth of the short bone pin 11.

[0089] After adjusting the adjusting block 6 to the appropriate height using the adjusting knob 12, tighten the bone pin adjusting knob screw 13 so that it engages with the threaded hole on the adjusting block 6 and firmly presses against the adjusting knob 12. Friction is used to limit the rotation of the adjusting knob 12, thereby locking the position of the adjusting block 6 and ensuring that it will not shift due to external force during subsequent bone fragment traction. For the short bone pin 11, after determining its implantation depth according to surgical requirements, tighten the fixing screw 7 to ensure its end is in close contact with the surface of the short bone pin 11. Pressure is used to fix the axial position of the short bone pin 11, preventing it from penetrating or exiting the bone under traction force. Through the synergistic action of these two screws, the adjusting block 6 can stably maintain the preset position, and the short bone pin 11 can firmly maintain the set implantation depth, providing reliable assurance for the precise operation of the traction mechanism. The bone pin adjusting knob screw 13 and the fixing screw 7 on the adjusting block 6 further improve the operational accuracy and fixation stability of the traction mechanism, providing double assurance for the controllability of the tibial transverse transport process. The bone pin adjustment knob screw 13 can precisely lock the rotation position of the adjustment knob 12 after the adjustment knob 12 drives the adjustment block 6 to the required position, avoiding displacement of the adjustment block 6 caused by accidental rotation of the adjustment knob 12 during surgery, ensuring the consistency of the bone block traction path, and reducing interference with angiogenesis caused by positional deviation; the fixed short bone pin screw 7 can firmly lock the implantation depth of the short bone pin 11, prevent the short bone pin 11 from sliding axially during traction, ensure the anchoring effect of the short bone pin 11 on the bone, avoid bone damage caused by unstable transmission of traction force, and improve the overall safety and reliability of the surgery.

[0090] In one embodiment, the hollow connecting rod 43 is connected to the traction mechanism via a connecting rod fixing clamp 9, and the connecting rod fixing clamp 9 is provided with a fixing screw 10 for the hollow connecting rod to achieve quick assembly and disassembly.

[0091] The connecting rod fixing clamp 9 serves as a connecting intermediary, fixedly connected to the fixing block 8 of the traction mechanism, providing a mounting base for the hollow connecting rod 43. When installing the hollow connecting rod 43, one end of the hollow connecting rod 43 is placed into the slot of the connecting rod fixing clamp 9, aligning its position with the traction mechanism. Then, the fixing screw 10 is tightened, and the locking force of the screw firmly fixes the hollow connecting rod 43 to the connecting rod fixing clamp 9, achieving a stable connection between the hollow connecting rod 43 and the traction mechanism. If it is necessary to disassemble or adjust the hollow connecting rod 43, the fixing screw 10 is rotated in the opposite direction to create a gap between it and the hollow connecting rod 43, allowing the hollow connecting rod 43 to be removed from the connecting rod fixing clamp 9 or its position adjusted. This process enables quick assembly and disassembly of the hollow connecting rod 43 and the traction mechanism, ensuring effective force transmission between the connecting rod mechanism 4 and the traction mechanism, and providing reliable support for the overall operation of the tibial transverse transport device. The hollow connecting rod 43 is connected to the traction mechanism via the connecting rod fixing clamp 9 and the fixing hollow connecting rod screw 10, which significantly improves the assembly efficiency and structural stability of the device. The connecting rod fixing clamp 9 provides precise connection positioning for the hollow connecting rod 43, ensuring accurate connection between the hollow connecting rod 43 and the traction mechanism and avoiding the transmission of influence due to connection deviation. The fixing hollow connecting rod screw 10 can quickly lock and loosen the hollow connecting rod 43, ensuring the firmness of the connection between the hollow connecting rod 43 and the traction mechanism during surgery, preventing bone fragment displacement errors caused by relative movement between the two, facilitating rapid preoperative assembly and postoperative disassembly, reducing surgical preparation and completion time, improving overall surgical efficiency, and providing convenience for subsequent maintenance or component replacement.

[0092] In one embodiment, the inner wall of the semi-circular clamp is provided with an elastic buffer layer to disperse the stress of the bone needle clamping.

[0093] A pair of semi-circular clamps open and close via a hinge. When the long bone needle 1 is placed between the clamps, the elastic buffer layer directly contacts the surface of the bone needle. Under the action of the locking mechanism, the two semi-circular clamps gradually close, and the elastic buffer layer deforms under compression, tightly wrapping the surface of the long bone needle 1. The reaction force generated by the deformation achieves flexible clamping of the bone needle. At this time, the elastic buffer layer evenly distributes the locking force to the contact surface of the bone needle, avoiding excessive local pressure. At the same time, it uses its own elasticity to compensate for minor unevenness on the surface of the bone needle, ensuring clamping stability. Through this process, the semi-circular clamps can firmly fix the long bone needle 1 and also disperse stress through the elastic buffer layer, providing a safe and reliable clamping environment for the bone needle. The elastic buffer layer design on the inner wall of the semi-circular clamps can effectively disperse the clamping stress on the long bone needle 1, significantly improving the safety and stability of bone needle fixation. The elastic buffer layer can conform to the surface of the long bone needle 1 through its own deformation, increasing the contact area and avoiding local stress concentration caused by traditional rigid clamping. This reduces micro-damage to the bone tissue around the bone needle caused by uneven force. At the same time, its elastic properties can absorb slight vibrations or traction fluctuations during the operation, preventing bone needle wear caused by rigid friction between the long bone needle 1 and the clamp. This ensures the stability of the bone needle during the transfer process, provides continuous and reliable support for the lateral movement of the bone block, and helps achieve the therapeutic effect of angiogenesis and microcirculation reconstruction.

[0094] In one embodiment, a lubricating coating is provided between the housing 33 and the clamping plate 34 to reduce the frictional resistance of omnidirectional rotation.

[0095] When the clamping screw 32 is rotated by the rotary wrench 31 to adjust the angle, the lubricating coating between the housing 33 and the clamping plate 34 comes into play, reducing the frictional resistance between the two relative movements. This allows the clamping plate 34 to move more smoothly with the clamping screw 32, making the angle adjustment process of the universal ball joint 23 more effortless and stable. Once the angle is determined, when the clamping screw 32 is tightened to lock the universal ball joint 23 with the clamping plate 34, the lubricating coating does not affect the contact and locking effect between the clamping plate 34 and the spherical surface of the universal ball joint 23. It only reduces frictional resistance during the adjustment phase, ensuring that the entire universal rotation mechanism 3 can both flexibly adjust the angle and stably lock, providing efficient support for the overall operation of the device. The lubricating coating design between the housing 33 and the clamping plate 34 effectively reduces the frictional resistance during the operation of the universal rotation mechanism 3, significantly improving the smoothness and flexibility of angle adjustment. The lubricating coating reduces the contact friction between the housing 33 and the clamping plate 34, allowing the clamping plate 34 to move more smoothly under the drive of the clamping screw 32. This avoids adjustment jamming or difficult operation caused by excessive friction, making the angle adjustment of the universal ball joint 23 easier and more precise. At the same time, the reduced friction loss extends the service life of the mechanism, ensuring stable adjustment performance during long-term use, providing reliable support for multi-angle bone pin implantation, and facilitating the smooth progress of surgery.

[0096] In one embodiment, all rotating adjustment components of the device are provided with anti-slip textures and scale markings.

[0097] When adjusting rotating components (such as adjusting knob 12, rotating wrench 31, connecting rod fastener 42, etc.), the anti-slip texture increases the friction of the contact surface, allowing the surgeon to grip and apply force more firmly, avoiding slippage that could lead to inadequate or excessive adjustment. Simultaneously, the scale markings clearly display the current adjustment amount, allowing the surgeon to precisely control the rotation angle or extension length according to surgical needs. For example, when adjusting the lifting bolt 5, the scale clearly indicates the lifting height of the adjusting block 6; when rotating the clamping screw 32, the scale indicates the clamping force. After adjustment, the anti-slip texture ensures that the components are not easily loosened by external force in a fixed state, while the scale markings provide a reference for subsequent checks or adjustments, ensuring that the adjustment and fixation of the entire device are always precise and controllable, facilitating a smooth surgical procedure.

[0098] One specific implementation of the tibial transverse transport device provided in this embodiment is as follows:

[0099] Before performing the surgery, assemble the traction mechanism. First, pass the rising bolt 5 through the hole between the fixing block 8, the adjusting knob 12, and the adjusting block 6 in sequence, and rotate the adjusting knob 12 to place the adjusting block 6 in the appropriate position. Then, install the bone pin adjusting knob screw 13 into the hole, leaving a gap for rotating the adjusting knob 12 without tightening it first. Finally, insert the two short bone pins 11 into the hole, adjust them to the appropriate position, and tighten the short bone pin fixing screws 7 on both sides to fix the short bone pins 11.

[0100] During the surgery, the long bone pins 1 on both sides are fixed, and the long bone pin clamping mechanism 2 is fixed to the long bone pins 1 on both sides. The fixing height is pre-adjusted, and the semi-circular clamp is locked with bolts. Next, the connecting rod fastener 42 is rotated to allow the solid connecting rod 41 to extend and retract freely. Its extension and retraction are controlled to a suitable length, and then the connecting rod fastener 42 is tightened to fix it. Then, the hollow connecting rod 43 is placed in a suitable position in the connecting rod fixing clamp 9, and the hollow connecting rod fixing screw 10 is rotated to fix it. Finally, the short bone pin 11 is fixed to the bone. At this time, the device is installed. The lateral movement of the bone can be completed by simply controlling the adjustment knob 12.

[0101] Although embodiments of the invention have been described in conjunction with the accompanying drawings, those skilled in the art can make various modifications and variations without departing from the spirit and scope of the invention, and such modifications and variations all fall within the scope defined by the appended claims.

Claims

1. A tibial transverse transport device, characterized in that, include: Traction mechanism; Two linkage mechanisms (4) are connected to both sides of the traction mechanism; Universal rotating mechanism (3) is provided at the end of the linkage mechanism (4); Long bone needle clamping mechanism (2) is provided at the end of the universal rotating mechanism (3); The traction mechanism is configured to drive the lateral displacement of the bone block, the linkage mechanism (4) includes a telescopic unit with adjustable length, and the universal rotation mechanism (3) realizes three-dimensional angle adjustment.

2. The tibial transverse transport device according to claim 1, characterized in that, The long bone needle clamping mechanism (2) includes: omnidirectional cue (23); A pair of semi-circular clamps connected by a hinge axis; The universal ball joint (23) is fixed to a semi-circular clamp on one side, and the other semi-circular clamp is fixed to the long bone needle (1) by a locking member.

3. The tibial transverse transport device according to claim 1, characterized in that, The linkage mechanism (4) includes: Hollow connecting rod (43); A solid connecting rod (41) nested within a hollow connecting rod (43); Link fastener (42) installed at the end of the hollow link (43); The connecting rod fastener (42) controls the extension and locking of the solid connecting rod (41) through a threaded connection.

4. The tibial transverse transport device according to claim 1, characterized in that, The universal rotating mechanism (3) includes: Outer shell (33); A clamping plate (34) is disposed within the outer casing (33); A clamping screw (32) that is threaded into the clamping plate (34); A rotary wrench (31) that drives the clamping screw (32); The clamping plate (34) makes spherical contact with the universal ball joint (23), and the universal angle is locked by tightening the clamping screw (32).

5. The tibial transverse transport device according to claim 1, characterized in that, The traction mechanism includes: Fixed block (8); The rising bolt (5) passes through the fixing block (8); Adjusting block (6) sleeved on the rising bolt (5); Adjustment knob (12) that drives the adjustment block (6) to rise and fall; Short bone needles (11) are fixed on both sides of the adjustment block (6).

6. The tibial transverse transport device according to claim 5, characterized in that, The adjusting block (6) is provided with: Bone pin adjustment knob screw (13) is used to lock the rotation position of the adjustment knob (12); The short bone pin screw (7) is used to fix the implantation depth of the short bone pin (11).

7. The tibial transverse transport device according to claim 3, characterized in that, The hollow connecting rod (43) is connected to the traction mechanism through the connecting rod fixing clamp (9), and the connecting rod fixing clamp (9) is provided with fixing screws (10) for the hollow connecting rod to achieve quick assembly and disassembly.

8. The tibial transverse transport device according to claim 2, characterized in that, The inner wall of the semi-circular clamp is provided with an elastic buffer layer to disperse the stress of the bone needle clamping.

9. The tibial transverse transport device according to claim 4, characterized in that, A lubricating coating is provided between the outer shell (33) and the clamping plate (34) to reduce the frictional resistance of omnidirectional rotation.

10. The tibial transverse transport device according to any one of claims 1-9, characterized in that, All rotating adjustment components of the device are equipped with anti-slip textures and scale markings.

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