A reduction and fixation assisting device for condylar head dislocation

Abstract

A reduction and fixation auxiliary device for free condylar fractures relates to the field of surgical instrument technology. This invention solves the problem of fragmentation in existing condylar fracture reduction instruments due to the inability to accurately determine the clamping force required for different patients. The invention comprises three clamping heads distributed circumferentially and each hinged to the jaw end of a clamping forceps via a rod. Each clamping head includes a clamping shell, a pressure sensor, and an elastic buffer block. The clamping shell has a groove, the pressure sensor is embedded in the bottom of the groove, and the elastic buffer block fills the groove and covers the pressure sensor. The clamping head contacts the fracture fragment through the elastic buffer block to buffer and transmit the clamping force. The pressure sensor is used to detect the clamping force on the elastic buffer block in real time. This invention is used for the reduction and fixation of free condylar fractures.

Description

Technical Field

[0001] This invention relates to the field of surgical instruments, specifically to a reduction and fixation auxiliary device for free condylar fractures. Background Technology

[0002] The mandibular condyle, a crucial component of the temporomandibular joint, is prominent in the face and relatively thin, making it prone to fracture. Intracapsular condylar fractures are a complex type of fracture, located deep within the jaw and adjacent to important nerves and blood vessels, resulting in extremely limited surgical space. After a fracture, due to the traction of the lateral pterygoid muscle, the free fracture fragments, especially the inner pole portion, often displace medially, anteriorly, and inferiorly. The key to clinical treatment lies in precisely reducing and stabilizing the displaced fracture fragments while preserving the attachment of the lateral pterygoid muscle as much as possible to facilitate fracture healing. However, in such a deep and narrow area, both counteracting strong muscle tension and performing delicate manipulations presents a significant challenge to the design of surgical instruments.

[0003] Currently, there are several specialized reduction devices for condylar fractures. For example, Chinese patent CN106994039A discloses a reduction and fixation clamp for condylar sagittal fractures. This device uses a positioning clamp head and a fastening clamp head design, which is intended to clamp the fracture fragments and protect the medial blood supply.

[0004] However, in practical applications, these instruments still have significant shortcomings. Their design focuses primarily on the initial "clamping and reduction" stage. When dealing with small, slippery free bone fragments within the condylar capsule that are under continuous traction from the lateral pterygoid muscle, the instruments often require a large clamping force to obtain sufficient clamping force to prevent slippage. However, the condylar surface is mainly composed of cancellous bone with relatively little compact bone, resulting in limited compressive strength. Excessive clamping force can easily crush the already fragile fracture fragments, causing iatrogenic injury and generating more bone fragments, thus increasing the complexity of the surgery and the risk of failure. Conversely, reducing the clamping force to avoid crushing makes it difficult to counteract muscle traction, resulting in inadequate fixation of the fracture fragments.

[0005] Another Chinese patent, CN203988297U, discloses a reduction clamp with a clamp head having a specific bending angle. The end of the clamp head has a fixed, widened rigid plate, designed to increase the contact area and distribute the clamping force to prevent bone fragment fracture. While this design can reduce the risk of bone fragment fracture to some extent, its rigid and non-adjustable plate surface still presents significant limitations when dealing with fracture patients with low compressive strength: the rigid plate surface makes hard contact with the fracture fragment, and insufficient contact area may lead to excessive local pressure and bone fracture; simultaneously, uneven distribution of clamping force may result in an inability to firmly grasp the fracture fragment. Furthermore, this structure cannot provide real-time feedback of clamping force, and the risk of fracture fragment fracture remains when the clamping force cannot be precisely adapted to the different clamping forces required by different patients.

[0006] In summary, existing condylar fracture reduction devices still suffer from fragmentation problems because they cannot accurately determine the clamping force required for different patients. Summary of the Invention

[0007] The purpose of this invention is to address the problem that existing condylar fracture reduction devices cannot accurately determine the clamping force required by different patients, resulting in the fragmentation of fracture pieces. Therefore, this invention provides a reduction and fixation auxiliary device for free condylar fractures.

[0008] The technical solution of this invention is:

[0009] This invention provides an auxiliary device for reduction and fixation of free condylar fractures, including clamping forceps, three clamping heads, and three rods. The three clamping heads are distributed circumferentially and are each hinged to the jaw end of the clamping forceps via one of the rods. Each clamping head includes a clamping housing, a pressure sensor, and an elastic buffer block. The clamping housing has a groove, the pressure sensor is embedded in the bottom of the groove, and the elastic buffer block fills the groove and covers the pressure sensor. The clamping head contacts the fracture fragment through the elastic buffer block to buffer and transmit the clamping force. The pressure sensor is used to detect the clamping force on the elastic buffer block in real time.

[0010] Furthermore, the clamping housing includes a clamping part and a hinge part detachably coaxially mounted to its end; both the clamping part and the hinge part are cylindrical housings, and the rear part of the clamping part is provided with an arc-shaped recess; one end of the rod passes through the clamping part and is connected to the jaw end, and the other end is a ball head; the hinge part adjusts the position of the clamping head by the degree of screwing.

[0011] Preferably, the elastic buffer block is a columnar buffer block, with its upper part being an arc-shaped contact surface for contacting the fracture fragments.

[0012] Preferably, the elastic buffer block includes an upper protruding contact block, an elastic cylinder, and a piston head; the elastic cylinder is embedded in the groove of the clamping housing, one end of the piston head contacts the upper protruding contact block located on the elastic cylinder, and the other end extends downward and contacts the pressure sensor.

[0013] Furthermore, the clamping pliers include a double-headed clamp arm and a single-headed clamp arm; the lower end of the double-headed clamp arm is provided with a handle, and the lower middle part is provided with a through groove; the lower end of the single-headed clamp arm is inserted into the through groove and is rotatably connected to the double-headed clamp arm through a rotating shaft; the jaw ends of the double-headed clamp arm and the single-headed clamp arm are respectively connected to the rod body.

[0014] Furthermore, it also includes a display mounted on the dual-headed or single-headed clamp arm and communicatively connected to the pressure sensor for displaying pressure data measured by the pressure sensor.

[0015] Furthermore, it also includes a jaw position adjustment unit, which includes an opening and closing adjustment screw, two blocks, and a fixing buckle; the two blocks are respectively fixedly installed on the same side of the double-headed jaw arm and the single-headed jaw arm and are arranged collinearly; the opening and closing adjustment screw is a double helix screw that passes through the two blocks, and by turning the opening and closing adjustment screw, the single-headed jaw arm can be moved closer to or away from the double-headed jaw arm; the fixing buckle is inserted on one of the blocks and is used to lock the position of the opening and closing adjustment screw.

[0016] Preferably, the opening and closing adjusting screw is provided with a screw head.

[0017] Furthermore, it also includes a locking mechanism, which comprises a locking block, a punched support rod, a limiting block, a screw positioning buckle, and a support rod positioning buckle; the locking block is sleeved on the smooth section in the middle of the opening and closing adjusting screw, and the screw positioning buckle passes through the locking block and abuts against the opening and closing adjusting screw; the punched support rod is perpendicular to the opening and closing adjusting screw and passes through the locking block, and the support rod positioning buckle passes through the locking block and abuts against the punched support rod; the limiting block is installed on the upper end face of the punched support rod near the clamping head, and the limiting block is provided with an anti-slip surface.

[0018] Furthermore, the locking mechanism also includes a shock-absorbing block, which is mounted on the perforated support rod and fits against the rear end face of the limiting block.

[0019] Compared with the prior art, the present invention has the following advantages:

[0020] 1. This invention achieves precise sensing and buffering control of the clamping force on bone fragments, fundamentally avoiding the risk of bone fragments being crushed during surgery.

[0021] This invention integrates a force sensing and buffering module, consisting of a pressure sensor and an elastic buffer block, into each independently hinged clamping head. When the clamping forceps close to grasp the loose fracture fragment, the three clamping heads contact the bone fragment surface through the elastic buffer blocks at their front ends. The elastic buffer blocks (whether integral cylindrical or a secondary buffer structure composed of elastic cylinders, etc.) can absorb and disperse local pressure, preventing stress concentration caused by rigid contact. Simultaneously, the clamping force acting on the buffer blocks is transmitted in real time to the pressure sensor for detection. The surgeon can accurately determine the magnitude of the currently applied clamping force by observing the values ​​on a display connected to the sensor, thereby actively controlling the clamping force within a safe threshold (determined by considering the patient's bone density and other factors) while ensuring stable reduction. This effectively solves the clinical dilemma of traditional instruments struggling to balance "insecure clamping" and "fragmenting too many fragments."

[0022] 2. This invention provides multi-degree-of-freedom adaptive clamping and reliable intraoperative temporary fixation, which significantly improves repositioning accuracy and operational stability.

[0023] This invention achieves multi-point envelope adaptive clamping of irregular fracture fragments through three independently hinged clamping heads and a matching posture adjustment mechanism. Specifically, each clamping head is connected to the end of the clamp arm via a rod, forming a ball joint or similar connection, allowing it to swing in multiple directions. Furthermore, the angle of each clamping head can be finely adjusted by screwing on the hinge of the clamping housing. This design allows the three clamping heads to better conform to the complex surface morphology of the fracture fragment, increasing the effective contact area and providing a more uniform and stable grip while reducing local pressure. After reduction, the jaw posture adjustment unit (especially the double-helix opening and closing adjustment screw) can be used to finely and stably adjust and lock the jaw opening, replacing the unreliable method of relying entirely on manual maintenance by an assistant in traditional surgery. This provides an extremely stable platform for the surgeon to perform subsequent internal fixation operations (such as drilling and nailing).

[0024] 3. This invention integrates high-precision drilling depth limiting and shock-absorbing guidance functions, greatly enhancing the safety and convenience of internal fixation procedures. The invention integrates a locking mechanism into the instrument body (i.e., the clamping forceps). This mechanism includes a drilling support rod, an adjustable limiting block, and a shock-absorbing block. During drilling, the drilling support rod can be extended to the surgical area, and the limiting block is pre-set at the precise depth the drill bit needs to reach. When the surgeon uses the bone-powered drilling system, the drill sleeve or drill bit itself can lean against the support rod and be mechanically blocked by the limiting block, thus physically preventing excessive drilling depth and completely avoiding the serious risks of drilling through the condylar cortex, damaging the glenoid fossa, or even intracranial tissues due to poor visibility or tactile deviation. Simultaneously, the shock-absorbing block effectively absorbs axial vibrations generated during drilling, reducing disturbance to the reduced bone fragments and further ensuring the stability of the operation and the reliability of the final fixation.

[0025] 4. This invention provides a multi-degree-of-freedom adaptive clamping and reliable intraoperative temporary fixation, which can achieve bidirectional stability and significantly improve repositioning accuracy and operational stability.

[0026] This invention achieves multi-point envelope adaptive clamping of irregular fracture fragments through three independently hinged clamping heads and a matching posture adjustment mechanism. Each clamping head is connected to the end of the clamp arm via a rod, forming a ball joint or similar connection, allowing it to swing in multiple directions. The angle of each clamping head can be finely adjusted by screwing on the hinged part of the clamping housing. This design allows the three clamping heads to better conform to the complex surface morphology of the fracture fragment, increasing the effective contact area and providing a more uniform and stable grip while reducing local pressure.

[0027] Furthermore, the three-point clamping layout and structural design of this invention enables bidirectional stable fixation of free fracture fragments. Along the jaw opening direction (which can be considered the X-axis), the three clamping heads work together to provide reliable clamping force to counteract the traction of soft tissues such as the lateral pterygoid muscle. Simultaneously, along the direction perpendicular to the clamp arm axis (which can be considered the Y-axis), the clamping heads form stable contact with the bone surface through their adaptive angle adjustment. Combined with the rigidity of the overall device, this effectively limits the displacement of the fracture fragment in this direction. After reduction, the jaw position adjustment unit (especially the double-helix opening and closing adjustment screw) can be used to finely and stably adjust and lock the jaw opening degree, replacing the unreliable method of relying entirely on manual maintenance by an assistant in traditional surgery. This provides three-dimensional fixation of the fracture fragment in both the X and Y directions, offering an extremely stable platform for the surgeon to perform subsequent internal fixation operations (such as drilling and nailing). Attached Figure Description

[0028] Figure 1 This is the front view of the present invention.

[0029] Figure 2This is an isometric view of the present invention.

[0030] Figure 3 This is a three-dimensional view of the rear view of the present invention.

[0031] Figure 4 This is a schematic diagram of the structure of the clamping head, rod, and clamp arm ends when the present invention adopts a two-stage buffer structure.

[0032] Figure 5 This is a top view of the two-stage buffer structure.

[0033] Figure 6 yes Figure 5 Sectional view along AA.

[0034] Figure 7 yes Figure 6 A 3D diagram.

[0035] Figure 8 This is a cross-sectional view of the clamping head when using an elastic buffer block.

[0036] Figure 9 yes Figure 8 A 3D diagram.

[0037] Figure 10 This is an exploded view of the clamping head and the rod.

[0038] Figure 11 This is a schematic diagram of the limit block and shock absorber installed on the drilled support rod.

[0039] In the picture:

[0040] 1. Clamping clamp; 101. Double-headed clamp arm; 102. Single-headed clamp arm; 103. Handle; 104. Through slot; 2. Clamping head; 201. Pressure sensor; 202. Elastic buffer block; 203. Clamping housing; 211. Upper protruding contact block; 222. Elastic cylinder; 223. Piston head; 231. Hinge part; 232. Clamping part; 233. Arc-shaped recess; 3. Rod body; 4. Display; 5. Opening and closing adjustment screw; 6. Block body; 7. Fixing buckle; 8. Tightening head; 9. Locking block; 10. Drilled support rod; 11. Limiting block; 12. Screw positioning buckle; 13. Support rod positioning buckle; 14. Shock absorber block. Detailed Implementation

[0041] Specific implementation method one: Combining Figures 1 to 10This embodiment describes a clamping pliers 1, which also includes three clamping heads 2 and three rods 3. The three clamping heads 2 are distributed circumferentially and are each hinged to the jaw end of the clamping pliers 1 via one of the rods 3. Each clamping head 2 includes a clamping housing 203, a pressure sensor 201, and an elastic buffer block 202. The clamping housing 203 has a groove, the pressure sensor 201 is embedded in the bottom of the groove, and the elastic buffer block 202 fills the groove and covers the pressure sensor 201. The clamping head 2 contacts the fracture fragment through the elastic buffer block 202 to buffer and transmit the clamping force. The pressure sensor 201 is used to detect the clamping force on the elastic buffer block 202 in real time.

[0042] This invention employs a three-point adaptive clamping design. During operation, three independently hinged clamping heads 2 contact and enclose the fracture fragments from different directions. The elastic buffer block 202 at the front end of each clamping head 2 adaptively deforms according to the subtle shape of the contact surface, thereby increasing the effective contact area and evenly distributing pressure. An embedded pressure sensor 201 monitors the force applied to the elastic buffer block 202 in real time and displays this value on the display 4 of the clamp arm. This allows the surgeon to quantify and actively control the clamping force, ensuring a firm grip while precisely controlling the force within a safe threshold. This fundamentally avoids the risk of crushing brittle fracture fragments due to improper force, providing crucial safety assurance for surgical procedures.

[0043] Furthermore, this three-point adaptive structure itself is an effective countermeasure against the lateral pterygoid muscle traction. The three gripping heads 2 are hinged to the clamp arms via their respective rods 3, allowing them to swing freely within a certain angle and automatically adapt to the fracture fragment surface at different angles due to muscle traction. This multi-directional mobility means the instrument does not need to forcibly dissect the lateral pterygoid muscle or use excessive force to "correct" the bone fragment, thus achieving stable initial grip and preliminary alignment with minimal soft tissue damage. This not only protects the blood supply to the fracture ends but also creates a favorable mechanical environment for subsequent precise reduction.

[0044] This device integrates three functions: repositioning, sensing, and temporary fixation. After initial grasping, the surgeon can use the opening and closing adjustment screw 5 on the forceps body to fine-tune and lock the opening and closing of the forceps jaws, ensuring the fracture fragment is firmly clamped in the preset position. This replaces the unstable state that requires an assistant to manually maintain throughout the entire procedure in traditional surgery, freeing the surgeon's hands and allowing them to focus on subsequent drilling and fixation operations. Simultaneously, the locking mechanism and drilling support rod 10 integrated into the forceps body provide stable depth limiting and guidance for the drill bit of the bone dynamics system, resolving the safety hazard of difficulty in controlling drilling depth under deep visualization, ensuring the safe and accurate implantation of internal fixation screws, and improving the overall controllability and safety of the surgery.

[0045] As a preferred embodiment, the elastic buffer block 202 is made of medical-grade silicone rubber, which can withstand temperatures above 200°C and is also compatible with various chemical disinfectants, facilitating disinfection, such as natural or synthetic rubber. The elastic buffer block 202 can be made of medical-grade silicone rubber with a Shore A hardness between 30 and 60. This hardness range provides sufficient softness for effective cushioning while also providing sufficient support to ensure stable force transmission.

[0046] Furthermore, due to the limited operating environment of this invention, the overall size of the clamping head 2 is relatively limited. Therefore, the pressure sensor 201 is preferably a fiber Bragg grating micro-force sensor, in which this fiber is embedded or adhered in a specific manner within a micro-groove at the bottom of the groove in the clamping housing 203. When the upper elastic buffer block 202 is compressed, the clamping housing 203 undergoes micro-strain, causing the fiber Bragg grating to shift its wavelength. The overall sensor size can be within 2mm, meeting the practical needs of precision medical instruments.

[0047] Specific Implementation Method Two: Combining Figure 4 , Figures 6 to 9 This embodiment describes a clamping housing 203 comprising a clamping portion 232 and a hinge portion 231 detachably and coaxially mounted to its end. Both the clamping portion 232 and the hinge portion 231 are cylindrical housings. The rear part of the clamping portion 232 is provided with an arc-shaped recess 233. One end of the rod 3 passes through the clamping portion 232 and is connected to the jaw end, while the other end is a ball head. The hinge portion 231 adjusts the position of the clamping head 2 by the degree of twisting.

[0048] This embodiment enables independent positional fine-tuning and rapid assembly / disassembly of each clamping head 2 in space, providing mechanical freedom for precise adaptation to complex bone block morphology during surgery.

[0049] In particular, the clamping housing 203 is designed as a separable clamping part 232 and a hinge part 231. The clamping part 232 can accommodate a force-measuring buffer module. Its rear arc-shaped recess 233 engages with the ball head at the end of the rod 3 to form a "ball-and-socket joint," which provides the clamping head 2 with basic omnidirectional swing freedom, allowing it to initially conform to the surface of the bone block. The hinge part 231 is coaxially screwed to the lower end of the clamping part 232 by threads. The depth of its screwing pushes or releases the internal ball head, thereby precisely changing the position of the ball head within the arc-shaped recess 233. By rotating the hinge part 231, the doctor can fine-tune the forward tilt, backward tilt, or lateral tilt angle of the clamping head 2 on a millimeter scale, achieving more precise "holding" or "hooking" actions on specific parts of the bone block, thereby achieving complex reduction.

[0050] As a preferred implementation, the connection between the hinge portion 231 and the clamping portion 232 is not limited to a thread; it can be replaced with a precision fine-tuning thread with a graduated ring to achieve quantitative adjustment. The mating surface between the arc-shaped recess 233 and the ball head can be treated with a titanium nitride coating to increase wear resistance and smoothness. To ensure stability after adjustment, an elastic anti-loosening washer can be provided between the hinge portion 231 and the clamping portion 232, or a fine-pitch thread with a self-locking function can be used.

[0051] Specific implementation method three: Combining Figures 8 to 9 This embodiment describes an elastic buffer block 202 as a columnar buffer block, with its upper part being an arc-shaped contact surface for contacting the fracture fragments.

[0052] This embodiment features a basic cylindrical buffer block (i.e., elastic buffer block 202) configuration, whose primary function is to provide a controllable and uniform initial interface for the transmission of clamping force. The arc-shaped contact surface is not merely for conforming to the bone block; its key function is to guide and converge the contact force. When the clamping head 2 contacts the irregular bone surface, the arc-shaped contact surface can guide the bone block to undergo slight sliding or rotation under the initial clamping force through line contact or small-area contact (unlike rigid multi-point rigid contact), thereby assisting it in automatically correcting itself to a more stable position and reducing the difficulty of precise alignment that relies entirely on the doctor's manual techniques.

[0053] As a preferred embodiment, the columnar buffer block (i.e., elastic buffer block 202) of this embodiment can be made of a gradient hardness material. For example, its core part uses a harder (Shore A 60°) medical-grade silicone to ensure force transmission efficiency, while the outer layer is wrapped with an extremely soft (Shore A 10° - 20°) silicone layer to form the arc-shaped contact surface, thereby maximizing contact adaptability while ensuring force sensing accuracy. In addition, the radius of curvature of the arc-shaped contact surface can be serialized according to the size of common condylar fracture fragments in clinical practice, for example, providing elastic buffer blocks 202 of different specifications such as R = 2mm, 3mm, and 4mm for selection during surgery.

[0054] Specific implementation method four: Combination Figure 4 , Figures 6 to 7 This embodiment describes an elastic buffer block 202 comprising an upper protruding contact block 211, an elastic cylinder 222, and a piston head 223. The elastic cylinder 222 is fitted into a groove in the clamping housing 203. One end of the piston head 223 contacts the upper protruding contact block 211 located on the elastic cylinder 222, and the other end extends downward and contacts the pressure sensor 201.

[0055] The elastic buffer block 202 in this embodiment is a two-stage buffer and force transmission structure. It enables segmented management and high-fidelity transmission of clamping force. The elastic cylinder 222, as a primary buffer unit, is responsible for absorbing and dispersing the initial impact and uneven pressure when in direct contact with the bone block, thus protecting fragile bone tissue. The piston head 223, as a relatively rigid force transmission medium, transmits the pressure, initially homogenized by the elastic cylinder 222, vertically to the pressure sensor 201 at the bottom with almost no loss. This combination of "soft contact - hard transmission" effectively isolates the influence of lateral shear force and torque caused by irregular contact surfaces or micro-movement of the bone block on the precision sensor, ensuring the high stability and accuracy of the force measurement signal.

[0056] As a preferred structure in this embodiment, the elastic cylinder 222 can adopt a variable wall thickness design, for example, the upper part is connected to the contact block (i.e., the upper protruding contact block 211) to provide greater initial compliance. The end of the piston head 223 that contacts the pressure sensor 201 can be machined into a micro-spherical surface to ensure point contact and eliminate lateral forces caused by installation misalignment. Alternatively, the elastic cylinder 222 and the piston head 223 can be integrated into a single dual-hardness structure, formed by one-time molding, with the upper part being made of ultra-soft silicone material to form the elastic cylinder 222 part, and the lower part being embedded or co-molded with a piston head 223 made of hard medical plastic or harder silicone. This reduces the number of parts, improves reliability, and avoids force loss from internal interfaces.

[0057] Specific Implementation Method Five: Combining Figures 1 to 3 This embodiment describes a clamping pliers 1 comprising a double-headed clamping arm 101 and a single-headed clamping arm 102. The lower end of the double-headed clamping arm 101 is provided with a handle 103, and the lower middle part is provided with a through groove 104. The lower end of the single-headed clamping arm 102 is inserted into the through groove 104 and is rotatably connected to the double-headed clamping arm 101 via a rotating shaft. The jaw ends of the double-headed clamping arm 101 and the single-headed clamping arm 102 are respectively connected to the rod body 3.

[0058] This embodiment transforms the rotational motion of the single-headed clamp arm 102 into the parallel opening and closing motion of the entire jaw relative to the frame of the double-headed clamp arm 101. This structure has higher rigidity and a more stable opening and closing trajectory than traditional cross-hinged clamps, which is beneficial for maintaining the preset clamping distance under complex tissue resistance.

[0059] The cross-section of the through groove 104 is preferably non-circular, such as rectangular or elliptical with guide keys, to precisely constrain the single-head clamp arm 102 and prevent it from twisting under force. The rotating shaft can be a preloaded, backlash-free bearing or a polymer self-lubricating bushing to ensure smooth rotation without play.

[0060] Specific Implementation Method Six: Combination Figures 1 to 3This embodiment further includes a display 4, which is mounted on the double-headed clamp arm 101 or the single-headed clamp arm 102 and is communicatively connected to the pressure sensor 201 to display the pressure data measured by the pressure sensor 201.

[0061] The display 4 in this embodiment transforms clamping force information from an invisible internal signal into intuitive visual feedback, providing the doctor with a force monitoring interface that is synchronized with hand operations and does not require shifting their gaze, thereby achieving precise "hand-eye coordination" operation. The display 4, mounted on the clamp arm, allows the doctor's line of sight to naturally extend along the instrument axis, enabling them to monitor force changes in real time with their peripheral vision while focusing on the surgical area. This breaks away from the traditional model that relies on tactile experience, making clamping force control a quantifiable and reproducible process.

[0062] Specific implementation method seven: Combining Figures 1 to 3 This embodiment further includes a jaw position adjustment unit, which comprises an opening / closing adjustment screw 5, two blocks 6, and a fixing buckle 7. The two blocks 6 are respectively fixedly installed on the same side of the double-headed jaw arm 101 and the single-headed jaw arm 102 and are arranged collinearly. The opening / closing adjustment screw 5 is a double-helix screw that passes through the two blocks 6. By turning the opening / closing adjustment screw 5, the single-headed jaw arm 102 can be moved closer to or away from the double-headed jaw arm 101. The fixing buckle 7 is inserted into one of the blocks 6 and is used to lock the position of the opening / closing adjustment screw 5.

[0063] The jaw position adjustment unit in this embodiment provides stable and reliable mechanical fine-tuning and locking capabilities for the jaw opening and closing, clearly separating the dynamic reset operation from the static maintenance and fixation stages. The design of the double-helix screw (i.e., the opening and closing adjustment screw 5) allows the operator to perform precise millimeter-level fine-tuning of the jaw opening and closing after initial reset and clamping, without continuously holding the handle 103 to maintain force. Instead, the operator can immediately lock the jaw opening and closing with the fixing buckle 7 by rotating the opening and closing adjustment screw 5. This achieves a transition from "forceful clamping" to "mechanical fixation," completely freeing the operator's hands and eliminating the risk of clamping force fluctuations due to muscle fatigue or unintentional relaxation, providing an absolutely stable base for subsequent delicate operations such as drilling.

[0064] As a preferred embodiment, the threads of the double-helix screw (i.e., the opening and closing adjustment screw 5) in this embodiment can adopt a differential thread design, that is, there is a slight difference in the pitch of the threads at both ends. In this way, when the opening and closing adjustment screw 5 rotates one revolution, the displacement of the two blocks 6 towards or away from each other is extremely small, thereby achieving ultra-fine adjustment resolution and meeting the stringent requirements for stable clamping of small bone blocks.

[0065] The fixing buckle 7 can be made of screws. By turning the screws and pressing the end of the screws against the opening and closing adjusting screw 5, quick locking and vibration resistance can be achieved.

[0066] Specific implementation method eight: Combination Figures 1 to 3 This embodiment describes an opening / closing adjustment screw 5 equipped with a screw head 8.

[0067] In this embodiment, the screw head 8 converts the minute movements of the rotating screw (i.e., the opening and closing adjustment screw 5) into operational inputs that can be precisely perceived and controlled by the fingers.

[0068] As a preferred embodiment, the shape of the screw head 8 is not limited to a conventional cylinder or hexagon. It can also be a knurled cylinder to increase friction for hand operation, or designed as a disc with radially symmetrical recesses to facilitate insertion with a matching L-shaped wrench, thereby providing greater torque and achieving more precise angle control. The surface of the screw head 8 can be treated with a matte or non-slip coating, such as medical-grade silicone, to ensure a firm grip in humid environments.

[0069] Specific Implementation Method Nine: Combining Figures 1 to 3 This embodiment further includes a locking mechanism, which comprises a locking block 9, a punched support rod 10, a limiting block 11, a screw positioning buckle 12, and a support rod positioning buckle 13. The locking block 9 is sleeved on the smooth section in the middle of the opening and closing adjusting screw 5, and the screw positioning buckle 12 passes through the locking block 9 and abuts against the opening and closing adjusting screw 5. The punched support rod 10 is perpendicular to the opening and closing adjusting screw 5 and passes through the locking block 9, and the support rod positioning buckle 13 passes through the locking block 9 and abuts against the punched support rod 10. The limiting block 11 is installed on the upper end face of the punched support rod 10 near the clamping head 2, and the limiting block 11 is provided with an anti-slip surface.

[0070] The locking mechanism in this embodiment is a drilling safety auxiliary platform that is independent of the clamping function and can be flexibly positioned in three-dimensional space. It provides an adjustable and stable external mechanical guide and depth limit for the drill bit of the bone power system. The locking block 9 can slide along the locked opening and closing adjustment screw 5, thereby positioning the entire drilling support system in a suitable front and rear position; the drilling support rod 10 can independently adjust its extension length and rotation angle; finally, by adjusting the height of the limit block 11 installed on the drilling support rod 10, a rigid physical stop point is set for the drill bit. This forms a set of personalized safe drilling solutions that can adapt to different surgical approaches and anatomical positions, transforming the drilling depth control, which originally relied entirely on the doctor's feel and experience, into a standardized operation that can be preset and mechanically guaranteed.

[0071] The contact surface between the limiting block 11 and the drill bit can be designed as a replaceable wear-resistant pad (such as high-molecular polyethylene) to avoid direct friction with the high-speed rotating drill bit metal, which would generate debris. The support rod positioning buckle 13 can be a fine-tuning knob with a scale display for easy locking of the drilling support rod 10. The locking method between the locking block 9 and the screw (i.e., the opening and closing adjusting screw 5), in addition to the positioning buckle (i.e., the screw positioning buckle 12), can be replaced with an eccentric cam locking mechanism with an operating handle to achieve quick locking and unlocking.

[0072] Specific Implementation Method Ten: Combining Figures 1 to 3 To illustrate this embodiment, the locking mechanism further includes a shock-absorbing block 14, which is mounted on the perforated support rod 10 and fits against the rear end face of the limiting block 11.

[0073] The shock absorber 14 in this embodiment introduces a controllable energy dissipation mechanism into the rigid limiting structure. It is used to absorb and isolate the axial impact and high-frequency vibration generated during drilling, preventing these harmful mechanical energies from being directly transmitted to the reduced fracture fragments and the entire clamping system through the support rod (i.e., the drilling support rod 10) and the locking mechanism. The shock absorber 14 ensures that the remaining kinetic energy of the drill bit is absorbed by the cushioning material at the moment it touches the limiting block 11, thereby avoiding instantaneous impact displacement of the bone fragments or disturbance to the precise adjustment state of the instrument that may be caused by rigid collision.

[0074] As a preferred embodiment, the damping block 14 can be made of silicone or polyurethane material with a high damping coefficient. Its contact with the rear end face of the limiting block 11 can be achieved through pre-compression installation, meaning that the damping block 14 is already compressed to a certain extent before the limiting block 11 is locked. This ensures that it functions effectively in the initial drilling stage, eliminating gaps. The shape of the damping block 14 can be designed as a hollow column or cone to optimize its deformation and energy absorption characteristics under axial pressure.

[0075] Combination Figures 1 to 11 Explanation of the working principle of this invention:

[0076] This invention provides a surgical device for condylar fractures that integrates reduction, force sensing, temporary fixation, and safe drilling assistance. Its working principle revolves around adaptive clamping and force feedback, mechanical locking stability, and safe drilling guidance.

[0077] 1. Adaptive clamping and force feedback

[0078] During the surgery, the surgeon operates the clamping forceps by holding the handle 103. The three clamping heads 2, hinged and supported by the rod 3, can swing in multiple directions, automatically conforming to the complex surface of the fracture fragment. When the jaws close, the elastic buffer block 202 (such as a cylindrical buffer block or an assembly consisting of an upper protruding contact block 211 and an elastic cylinder 222) at the front end of each clamping head 2 contacts the bone fragment. The elastic buffer block 202 deforms, buffering local pressure and increasing the contact area. Simultaneously, the clamping force is transmitted through the buffer block to the pressure sensor 201 at its bottom. The pressure sensor 201 converts the force signal into an electrical signal, which is transmitted to the display 4 mounted on the forceps arm for real-time display. Based on the displayed force value, the surgeon precisely controls the clamping force within a safe range while ensuring a firm grip, thereby avoiding crushing the bone fragment.

[0079] 2. Mechanical locking stability

[0080] After reduction, the surgeon no longer needs to continuously hold the handle 103 to apply force. The double-helix screw is driven to rotate by rotating the screw head 8 on the opening / closing adjustment screw 5. Since the opening / closing adjustment screw 5 passes through two blocks 6 respectively fixed to the double-headed clamp arm 101 and the single-headed clamp arm 102, the rotation of the screw causes the single-headed clamp arm 102 to produce a fine linear displacement relative to the double-headed clamp arm 101, thereby slightly adjusting the opening degree of the clamp jaws to the optimal fixation position. After adjustment, the fixing buckle 7 is tightened to firmly lock the opening / closing adjustment screw 5. At this point, the fracture fragment is stably clamped between the three clamping heads 2, and the entire device forms a rigid temporary fixation support, freeing the surgeon's hands.

[0081] 3. Drilling safety guidance

[0082] Before drilling for internal fixation, the surgeon first assembles the locking mechanism. The locking block 9 is fitted onto the middle of the locked opening / closing adjusting screw 5, slids it to the appropriate position, and then locks it with the screw positioning buckle 12. The drilling support rod 10 is inserted perpendicularly to the opening / closing adjusting screw 5 into the locking block 9. After adjusting its extension length and angle, it is locked with the support rod positioning buckle 13. Finally, according to the required drilling depth as planned preoperatively or measured intraoperatively, the height of the limiting block 11 is set on the drilling support rod 10 and fixed. The rear end face of the limiting block 11 is fitted with a shock-absorbing block 14. When the surgeon uses the bone dynamics system to drill, the drill bit advances along the direction of the drilling support rod 10, and its axial depth is mechanically blocked by the limiting block 11, thus preventing excessive drilling depth. The impact and vibration generated during drilling are absorbed by the shock-absorbing block 14, avoiding disturbance to the reduced fracture fragments.

[0083] The above embodiments are only used to illustrate the technical solutions of the present invention, and are not intended to limit it. Although the present invention has been described in detail with reference to the foregoing embodiments, those skilled in the art should understand that modifications can still be made to the technical solutions described in the foregoing embodiments, or equivalent substitutions can be made to some of the technical features. Such modifications or substitutions do not cause the essence of the corresponding technical solutions to deviate from the spirit and scope of the technical solutions of the embodiments of the present invention.

Claims

1. A reduction and fixation auxiliary device for free condylar fractures, comprising clamping forceps (1), characterized in that: It also includes three clamping heads (2) and three rods (3); the three clamping heads (2) are distributed circumferentially and are respectively hinged to the jaw end of the clamping pliers (1) through one of the rods (3); each clamping head (2) includes a clamping housing (203), a pressure sensor (201) and an elastic buffer block (202); the clamping housing (203) is provided with a groove, the pressure sensor (201) is embedded in the bottom of the groove, and the elastic buffer block (202) fills the groove and covers the pressure sensor (201); the clamping head (2) contacts the fracture fragment through the elastic buffer block (202) to buffer and transmit the clamping force, and the pressure sensor (201) is used to detect the clamping force on the elastic buffer block (202) in real time.

2. The reduction and fixation auxiliary device for free condylar fractures according to claim 1, characterized in that: The clamping housing (203) includes a clamping part (232) and a hinge part (231) detachably coaxially mounted at its end; both the clamping part (232) and the hinge part (231) are cylindrical housings, and the rear part of the clamping part (232) is provided with an arc-shaped recess (233); one end of the rod (3) passes through the clamping part (232) and is connected to the jaw end, and the other end is a ball head. The hinge part (231) adjusts the position of the clamping head (2) by the degree of twisting.

3. The reduction and fixation auxiliary device for free condylar fractures according to claim 2, characterized in that: The elastic buffer block (202) is a columnar buffer block with an arc-shaped contact surface on its upper part for contacting the fracture fragments.

4. The reduction and fixation auxiliary device for free condylar fractures according to claim 2, characterized in that: The elastic buffer block (202) includes an upper protruding contact block (211), an elastic cylinder (222), and a piston head (223); the elastic cylinder (222) is embedded in the groove of the clamping housing (203), one end of the piston head (223) contacts the upper protruding contact block (211) located in the elastic cylinder (222), and the other end extends downward and contacts the pressure sensor (201).

5. The reduction and fixation auxiliary device for free condylar fractures according to claim 2, characterized in that: The clamping pliers (1) include a double-headed clamp arm (101) and a single-headed clamp arm (102); the lower end of the double-headed clamp arm (101) is provided with a handle (103), and the middle and lower part is provided with a through groove (104); the lower end of the single-headed clamp arm (102) is inserted into the through groove (104) and is rotatably connected to the double-headed clamp arm (101) through a rotating shaft; the jaw ends of the double-headed clamp arm (101) and the single-headed clamp arm (102) are respectively connected to the rod body (3).

6. The reduction and fixation auxiliary device for free condylar fractures according to claim 5, characterized in that: It also includes a display (4), which is mounted on the double-headed clamp arm (101) or the single-headed clamp arm (102) and is communicatively connected to the pressure sensor (201) for displaying the pressure data measured by the pressure sensor (201).

7. The reduction and fixation auxiliary device for free condylar fractures according to claim 5, characterized in that: It also includes a jaw position adjustment unit, which includes an opening and closing adjustment screw (5), two blocks (6) and a fixing buckle (7). The two blocks (6) are respectively fixedly installed on the same side of the double-headed clamp arm (101) and the single-headed clamp arm (102) and are arranged collinearly; The opening and closing adjustment screw (5) is a double helical screw that passes through the two blocks (6). By turning the opening and closing adjustment screw (5), the single-head clamp arm (102) can be driven to move closer to or away from the double-head clamp arm (101). The fixing buckle (7) is installed on one of the blocks (6) to lock the position of the opening and closing adjustment screw (5).

8. The reduction and fixation auxiliary device for free condylar fractures according to claim 7, characterized in that: The opening and closing adjusting screw (5) is provided with a screw head (8).

9. The reduction and fixation auxiliary device for free condylar fractures according to claim 8, characterized in that: It also includes a locking mechanism, which includes a locking block (9), a punched support rod (10), a limiting block (11), a screw positioning buckle (12), and a support rod positioning buckle (13). The locking block (9) is sleeved on the smooth rod section in the middle of the opening and closing adjusting screw (5), and the screw positioning buckle (12) passes through the locking block (9) and abuts against the opening and closing adjusting screw (5). The punched support rod (10) is perpendicular to the opening and closing adjusting screw (5) and passes through the locking block (9). The support rod positioning buckle (13) passes through the locking block (9) and abuts against the punched support rod (10). The limiting block (11) is installed on the upper end face of the punched support rod (10) near the clamping head (2), and the limiting block (11) is provided with an anti-slip surface.

10. The reduction and fixation auxiliary device for free condylar fractures according to claim 9, characterized in that: The locking mechanism also includes a shock absorber (14), which is mounted on the perforated support rod (10) and fits against the rear end face of the limiting block (11).

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