Knee immobilization support training apparatus and method

Abstract

The application discloses a knee fixing and supporting training device and a training method, relates to the technical field of physiotherapy devices, and comprises a wearing mechanism to be worn on the waist of a human body, wherein the wearing mechanism comprises a binding belt, a left support and a right support, one end of the left support is hingedly connected to the end of the right support, the binding belt is connected with the left support and the right support respectively, and the binding belt is used for connecting the waist of the human body; the left support and the right support are both provided with a training mechanism for knee rehabilitation, any training mechanism comprises a first supporting arm fixed to a calf and a second supporting arm fixed to a thigh, the first supporting arm and the second supporting arm are connected through an angle limiting piece, and a buffer element is arranged between the first supporting arm and the second supporting arm. The knee fixing and supporting training device can accurately limit the maximum bending angle of the thigh and the calf through the angle limiting piece, can adapt to the normal activity range according to the postoperative recovery stage of a patient, can flexibly adjust the maximum bending angle, and can avoid secondary stress on the damaged part due to an excessively large angle.

Description

Technical Field

[0001] This invention relates to the field of physiotherapy equipment technology, specifically to a knee fixation support training device and training method. Background Technology

[0002] In the fields of clinical medicine and rehabilitation, patients with knee injuries such as cruciate ligament tears, meniscus injuries, and patellar dislocations, as well as those undergoing postoperative rehabilitation after knee replacement surgery or ligament repair surgery, and those with degenerative diseases such as osteoarthritis, all need to restore the stability, range of motion, and muscle strength of the knee joint through scientific fixation and progressive training to avoid complications such as joint stiffness and muscle atrophy caused by prolonged immobilization. Traditional static fixation devices, such as knee braces and splints, mostly use elastic bandages or rigid plastic shells. They can only provide basic wrapping and fixation for the knee joint, and cannot adjust the range of motion of the knee joint according to the needs of the patient's rehabilitation stage. They also lack targeted support for the thigh and lower leg, and are prone to displacement when the patient stands or moves slightly. This not only affects the fixation effect, but may also cause poor blood circulation due to local pressure, increasing the patient's discomfort. They also cannot adaptively adjust to the patient's specific condition, rehabilitation stage, and physical condition during rehabilitation operations, thus limiting their scope of use. In addition, the patient's knee flexion and extension rate changes in real time. Traditional devices cannot adjust the damping according to the rate. If the rate is too fast, the cushioning is insufficient and may impact the joint. If the rate is too slow, the cushioning is too strong and affects the training efficiency. Summary of the Invention

[0003] In order to solve the technical problems existing in the prior art, this application provides a knee fixation support training device and training method.

[0004] To achieve the above objectives, the technical solution adopted in this application is as follows: a knee fixation support training device, comprising: a wearable mechanism worn on the waist of a person, the wearable mechanism including a binding strap, a left support and a right support, one end of the left support being hinged to the end of the right support, the binding strap being connected to the left support and the right support respectively, and the binding strap being used to connect to the waist of the person; both the left support and the right support are provided with a training mechanism for knee rehabilitation, each training mechanism including a first arm fixed to the lower leg and a second arm fixed to the thigh, the first arm and the second arm being connected by an angle limiting member, the angle limiting member being used to limit the maximum bending angle of the first arm and the second arm; a buffer element is provided between the first arm and the second arm.

[0005] In some embodiments of the present invention, the angle limiting member includes a base disposed on the second arm, a rotating shaft fixed to the first arm, a synchronizing block and a limiting post. The rotating shaft is rotatably disposed on the base, the synchronizing block is disposed at the end of the rotating shaft extending out of the base, the outer side of the base has a plurality of limiting slots, the limiting post can extend into any limiting slot, and the synchronizing block can abut against the limiting post under the synchronous rotation of the rotating shaft.

[0006] In some embodiments of the present invention, the buffer element includes a buffer rod and a solenoid valve for adjusting the air intake of the buffer rod. The buffer rod includes a sleeve and a slide rod. One end of the sleeve is hinged to a first support arm, one end of the slide rod extends into the sleeve away from the first support arm, and the other end of the slide rod is hinged to a second support arm. The slide rod and the sleeve are connected with a clearance fit. A vent hole is provided on the sleeve, and the solenoid valve is disposed on the vent hole.

[0007] In some embodiments of the present invention, both the first arm and the second arm are provided with fixing members. The fixing members include a mounting ring and an airbag. The airbag is circumferentially disposed on the inner sidewall of the mounting ring, and the inner sidewall of the airbag can abut against human skin.

[0008] In some embodiments of the present invention, the airbag is provided with an air inlet for inflation or deflation, and the air inlet can be connected to an inflation device.

[0009] In some embodiments of the present invention, the two ends of the binding strap are connected by a detachable component, which includes a Velcro strap. The Velcro strap includes a sub-strap disposed at one end of the binding strap and a main strap disposed at the other end of the binding strap, and the sub-strap can be attached to the main strap.

[0010] In some embodiments of the present invention, the first arm includes a limiting cylinder and an adjusting rod. The adjusting rod is slidably disposed inside the limiting cylinder. The limiting cylinder is provided with a plurality of first through holes. The adjusting rod is provided with second through holes at uniform intervals. The central axis of any first through hole may coincide with the central axis of any second through hole.

[0011] The present invention also provides a knee training method using a knee fixation support training device, comprising the following steps: S101: Based on the patient's knee injury type and rehabilitation stage, set the target buffer level of the buffer bar, and preset the air pressure fluctuation threshold range in the sleeve for different buffer levels. The pre-set threshold for air pressure fluctuation in the early postoperative period is 0.04-0.07×10⁻⁶. 5 Pa, recovery period is 0.05-0.08×10 5 Pa, with a functional reconstruction period of 0.08-0.10×10 5 Pa; S102: The sensor installed at the pivot of the angle limiting component collects the relative rotational angular velocity between the first and second arms during the flexion and extension of the knee joint. At the same time, the air pressure sensor installed on the inner wall of the sleeve collects the dynamic air pressure value inside the sleeve in real time. S103: Calculate the knee flexion-extension rate based on the collected relative rotational angular velocity. If the flexion-extension rate is greater than the preset threshold, it is determined that the cushioning effect needs to be enhanced; if the flexion-extension rate is less than the preset threshold, it is determined that the cushioning effect needs to be weakened. S104: Based on the buffering requirement, adjust the airflow state of the vent: When the buffering needs to be enhanced, control the airflow of the vent through the solenoid valve, reduce the venting cross-sectional area, reduce the air discharge or intake rate in the sleeve, and increase the sliding damping of the slide rod; when the buffering needs to be weakened, control the airflow of the vent through the solenoid valve to increase the airflow, accelerate the airflow in the sleeve, and reduce the sliding damping of the slide rod. S105: Continuously collect the air pressure value inside the sleeve and the knee flexion and extension rate, compare the real-time air pressure value with the preset air pressure fluctuation threshold. If the real-time air pressure value exceeds the threshold range, repeat step S104 to adjust the airflow state of the vent until the air pressure value stabilizes within the preset threshold, so as to achieve dynamic adaptation of the buffering effect.

[0012] In some embodiments of the present invention, in step S101 above, the buffer level is correlated with the patient's weight. When the patient's weight is ≥80kg, the air pressure fluctuation threshold for the corresponding rehabilitation stage is increased by 15%-20%; when the patient's weight is ≤40kg, the air pressure fluctuation threshold for the corresponding rehabilitation stage is decreased by 10%-15%.

[0013] In some embodiments of the present invention, S106 is further included: when the gas pressure inside the sleeve suddenly exceeds 0.3 × 10⁻⁶, 5 Pa or below 0.04 × 10 5 When Pa occurs, immediately control the solenoid valve to fully open the vent, and simultaneously trigger the buzzer alarm to prevent abnormal damping of the buffer rod from impacting the knee joint. Beneficial effects

[0014] 1. A wearable mechanism worn around the waist combines a left and right support frame with a binding strap. The left and right supports are hinged to fit the contours of the waist, while the binding strap provides a tight fit and reliable fixation, establishing a coordinated support system for the waist and lower limbs. When patients perform standing, walking, or flexion / extension exercises, the lumbar support mechanism provides a stable support base, effectively preventing equipment displacement due to lower limb movements. Simultaneously, through the coordinated force transmission between the waist and lower limbs, it reduces the compensatory burden on the waist caused by the patient's efforts to maintain balance, lowering the risk of secondary injuries such as lower back pain and postural deformities. It is particularly suitable for elderly patients or those with pre-existing lumbar strain, significantly improving the safety and comfort of the rehabilitation process.

[0015] 2. In the training device, the first and second arms are connected by an angle limiting device. This device precisely limits the maximum bending angle of both arms. It allows for flexible adjustment of the maximum bending angle based on the patient's needs: strict angle limitation in the early postoperative period, gradual angle expansion during recovery, and adaptation to normal range of motion during functional reconstruction. This avoids secondary stress on the injured area due to excessive angle, while also preventing insufficient angle from hindering joint mobility recovery. The stable limiting function of the angle limiting device allows the device to adapt to the rehabilitation needs of different injury types, such as cruciate ligament tears, meniscus injuries, and post-knee replacement surgery, providing patients with scientific and progressive training support and accelerating the rehabilitation process.

[0016] 3. Differentiated air pressure thresholds are set based on the rehabilitation stage, from low buffering in the early postoperative period to high buffering during the functional reconstruction period, to meet the rehabilitation needs of different stages. The air pressure thresholds are adjusted in combination with weight to avoid excessive or insufficient buffering due to weight differences, thus covering more patients in a wider weight range.

[0017] 4. Real-time acquisition of flexion and extension rates and air pressure values, and dynamic adjustment of damping by adjusting the cross-sectional area of ​​the ventilation holes: enhanced buffering and shock protection when the rate is fast, and reduced buffering efficiency when the rate is slow, making the training process more stable. Continuous monitoring of air pressure and closed-loop adjustment to ensure that the air pressure is stable within the preset threshold, avoiding fluctuations in the buffering effect from affecting the training quality. Attached Figure Description

[0018] To more clearly illustrate the technical solutions in the embodiments of this application or the prior art, the drawings used in the description of the embodiments or the prior art will be briefly introduced below. Obviously, the drawings described below are only some embodiments of this application. For those skilled in the art, other drawings can be obtained based on these drawings without creative effort.

[0019] Figure 1 This is a structural illustration of an embodiment of this application. Figure 1 ; Figure 2 This is a structural illustration of an embodiment of this application. Figure 2 ; Figure 3 for Figure 2 A magnified view of a section at point A in the middle; Figure 4 This is a schematic diagram of the wearable mechanism structure according to an embodiment of this application; Figure 5 This is a schematic diagram of the buffer rod structure according to an embodiment of this application. Figure 1 ; Figure 6 This is a schematic diagram of the first support arm structure according to an embodiment of this application; Figure 7 This is a schematic diagram of the buffer rod structure according to an embodiment of this application. Figure 2 .

[0020] In the diagram: 1-Binding strap; 2-Left bracket; 3-Right bracket; 4-First support arm; 401-Adjusting rod; 402-Limiting cylinder; 5-Second support arm; 6-Angle limiting component; 601-Base; 602-Rotating shaft; 603-Synchronizing block; 604-Limiting post; 7-Limiting slot; 8-Buffer rod; 801-Sleeve; 802-Slide rod; 9-Ventilation hole; 10-Fixing component; 1001-Mounting ring; 1002-Airbag; 11-Air nozzle; 12-Hook and loop fastener; 1201-Daughter strap; 1202-Main strap; 13-First through hole; 14-Second through hole; 15-Solenoid valve; 16-Pressure sensor. Detailed Implementation

[0021] To make the objectives, technical solutions, and advantages of the embodiments of this application clearer, the technical solutions of the embodiments of this application will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only some embodiments of this application, and not all embodiments. The components of the embodiments of this application described and shown in the accompanying drawings can generally be arranged and designed in various different configurations.

[0022] Therefore, the following detailed description of the embodiments of this application provided in the accompanying drawings is not intended to limit the scope of the claimed application, but merely to illustrate selected embodiments of the application. All other embodiments obtained by those skilled in the art based on the embodiments of this application without inventive effort are within the scope of protection of this application.

[0023] It should be noted that similar labels and letters in the following figures indicate similar items. Therefore, once an item is defined in one figure, it does not need to be further defined and explained in subsequent figures.

[0024] In the description of this application, it should be noted that the use of terms such as "center," "upper," "lower," "left," "right," "vertical," "horizontal," "inner," and "outer" to indicate orientation or positional relationships is based on the orientation or positional relationships shown in the accompanying drawings, or the orientation or positional relationships commonly used when the product is in use. These terms are used solely for the convenience of describing this application and for simplifying the description, and do not indicate or imply that the device or element referred to must have a specific orientation, or be constructed and operated in a specific orientation. Therefore, they should not be construed as limitations on this application. Furthermore, the use of terms such as "first" and "second" in the description of this application is only used to distinguish descriptions and should not be construed as indicating or implying relative importance.

[0025] Furthermore, the use of terms such as "horizontal" and "vertical" in the description of this application does not imply that the component is required to be absolutely horizontal or suspended, but rather that it may be slightly tilted. For example, "horizontal" simply means that its direction is more horizontal relative to "vertical," and does not mean that the structure must be completely horizontal, but rather that it may be slightly tilted.

[0026] In the description of this application, it should also be noted that, unless otherwise expressly specified and limited, the terms "set up," "install," "connect," and "link" should be interpreted broadly. For example, they can refer to a fixed connection, a detachable connection, or an integral connection; they can refer to a mechanical connection or an electrical connection; they can refer to a direct connection or an indirect connection through an intermediate medium; and they can refer to the internal connection between two components. Those skilled in the art can understand the specific meaning of the above terms in this application based on the specific circumstances. Example

[0027] Please refer to Figures 1-7 This embodiment provides a knee fixation and support training device, including: a wearable mechanism worn on the waist of a person, the wearable mechanism including a binding strap 1, a left support 2 and a right support 3, one end of the left support 2 is hinged to the end of the right support 3, the binding strap 1 is connected to the left support 2 and the right support 3 respectively, and the binding strap 1 is used to connect the waist of the person; both the left support 2 and the right support 3 are provided with a training mechanism for knee rehabilitation, each training mechanism including a first arm 4 fixed to the lower leg and a second arm 5 fixed to the thigh, the first arm 4 and the second arm 5 are connected by an angle limiting member 6, the angle limiting member 6 is used to limit the maximum bending angle of the first arm 4 and the second arm 5; a buffer element is provided between the first arm 4 and the second arm 5.

[0028] In this embodiment, the left support 2 and the right support 3 are connected at one end by a hinge structure to form an openable lumbar support frame. The hinge point can rotate flexibly around the axis, allowing the left and right supports 3 to adjust their opening angle according to the width of the patient's waist. When the patient wears the support, the left support 2 conforms to the left side of the waist contour, and the right support 3 conforms to the right side of the waist contour. The hinge structure can adapt to the waist curves of patients with different body types, avoiding gaps or excessive compression between the support and the waist. As rigid support components, the left support 2 and the right support 3 can transmit the force from the lower limb training mechanism to the waist, forming a force transmission path between the waist and the lower limbs, rather than letting the knee joint bear the pressure alone.

[0029] In this embodiment, the binding strap 1 is made of highly elastic and breathable fabric, and both ends are fixed by detachable structures to form a fastening ring around the waist. When the patient wears it, he first adjusts the opening angle of the left and right supports 3 to fit the waist, and then adjusts the tightness by tightening the binding strap 1 so that the supports fit the waist tightly without compressing the blood vessels in the waist. The elasticity of the binding strap 1 can adapt to the patient's breathing, bending and other slight movements, avoiding discomfort caused by rigid fixation. At the same time, its breathable fabric can reduce the heat and sweating of the waist skin and improve the comfort of wearing it for a long time.

[0030] In this embodiment, both the first arm 4 and the second arm 5 are made of carbon fiber and conform to the contours of the lower leg and thigh. Their connection is as follows: the lower ends of the first arm 4 and the second arm 5 are hinged together by an angle limiting member 6, forming a "mobile joint" that can rotate around the knee joint. When the patient flexes and extends the knee joint, the first arm 4 moves synchronously with the lower leg, and the second arm 5 moves synchronously with the thigh. The rigid structure of the arms restricts abnormal knee joint movement while transmitting the limiting force of the angle limiting member 6.

[0031] The angle limiting component 6 is a mechanical limiting structure with different angle adjustments. The surface of the limiting component is marked with angle scales of 0°, 30°, 60° and 90°. The maximum bending angle can be set by adjusting the position of the pin, such as 30° in the early postoperative period, 60° in the recovery period and 90° in the functional reconstruction period. When the knee joint flexes or extends to the set angle, the positioning pin inside the limiting component will engage with the corresponding angle slot, restricting the first arm 4 and the second arm 5 from continuing to rotate relative to each other, thereby preventing excessive bending of the knee joint. If the angle needs to be adjusted, simply press the unlock button to release the positioning pin and rotate the knob to set a new angle. The operation is simple and requires no professional tools. The maximum bending angle can be flexibly adjusted according to the patient's postoperative recovery progress, avoiding recurrence of injury due to excessive angle or affecting the recovery of range of motion due to insufficient angle. Compared with the "manual coarse adjustment" of existing equipment, the angle control accuracy is improved to ±2°, meeting the differentiated needs of different rehabilitation stages.

[0032] It should be noted that the first arm 4 and the second arm 5 of the training device fix the lower leg and thigh, restricting the knee joint movement within a controllable range; the angle limiting component 6 sets the maximum bending angle of the knee joint according to rehabilitation needs, ensuring that the training is safe and effective.

[0033] The aforementioned buffer element is used to provide real-time protection when the first arm 4 and the second arm 5 rotate relative to each other, so as to avoid secondary injury during rehabilitation therapy.

[0034] Please refer to Figure 1 and Figure 2In some embodiments of this example, the angle limiting member 6 includes a base 601 disposed on the second support arm 5, a rotating shaft 602 fixed to the first support arm 4, a synchronizing block 603 and a limiting post 604. The rotating shaft 602 is rotatably disposed on the base 601, and the synchronizing block 603 is disposed at the end of the rotating shaft 602 that extends out of the base 601. The outer side of the base 601 has a plurality of limiting slots 7, and the limiting post 604 can extend into any of the limiting slots 7. The synchronizing block 603 can abut against the limiting post 604 under the synchronous rotation of the rotating shaft 602.

[0035] In this embodiment, the base 601 is made of ABS resin and has a "U"-shaped groove structure. It is fixed to the lower end of the second arm 5 by welding and serves as the fixing part of the angle limiting member 6. The inner side of the "U"-shaped groove of the base 601 is provided with a bearing hole for installing the rotating shaft 602, ensuring that the rotating shaft 602 can rotate flexibly around the bearing hole without significant shaking. The rotating shaft 602 is a cylindrical metal part, which is fixed to the upper end of the first arm 4 by welding. The other end passes through the bearing hole of the base 601 and extends out of the outside of the base 601, forming a "rotation connecting shaft". When the patient's knee joint flexes and extends, the first arm 4 moves synchronously with the lower leg, driving the rotating shaft 602 to rotate around the bearing hole of the base 601. The fit clearance between the rotating shaft 602 and the bearing hole is controlled at 0.1-0.2mm, which ensures smooth rotation and avoids angle deviation caused by excessive clearance. Meanwhile, the synchronizing block 603 is a metal block whose radius coincides with that of the base 601. When the rotating shaft 602 drives the synchronizing block 603 to rotate, the abutting edge will move closer to or further away from the limiting post 604 as the rotation angle changes. When the knee joint is bent to the set angle, the abutting edge of the synchronizing block 603 just contacts the side of the limiting post 604 that extends into the limiting slot 7. Since the synchronizing block 603 is fixed to the rotating shaft 602, the subsequent rotation of the rotating shaft 602 will be blocked by the limiting post 604, thereby limiting the relative rotation angle between the first arm 4 and the second arm 5, that is, locking the maximum bending angle of the knee joint.

[0036] The aforementioned limiting post 604 is a cylindrical metal part with a diameter that matches the diameter of the upper limit slot 7 on the base 601. When adjusting the angle, the user first pulls the limiting post 604 outward to disengage it from the current upper limit slot 7. Then, according to the requirements, the user rotates the angle of the first arm 4, observes the angle scale on the base 601, and inserts the limiting post 604 into the corresponding upper limit slot 7. This makes angle changes more convenient.

[0037] Please refer to Figure 1 , Figure 2 as well as Figure 7In some embodiments of this example, the buffer element includes a buffer rod 8 and a solenoid valve 15 for adjusting the air intake of the buffer rod 8. The buffer rod 8 includes a sleeve 801 and a slide rod 802. One end of the sleeve 801 is hinged to the first support arm 4, one end of the slide rod 802 extends into the sleeve 801 away from the first support arm 4, and the other end of the slide rod 802 is hinged to the second support arm 5. The slide rod 802 and the sleeve 801 are connected with a clearance fit. A vent hole 9 is provided on the sleeve 801, and the solenoid valve 15 is provided on the vent hole 9.

[0038] In this embodiment, the aforementioned buffer rod 8 serves as a dynamic buffer component between the first arm 4 and the second arm 5. Through the structural cooperation of the sleeve 801, the slide rod 802, and the vent 9, it provides flexible buffering force during the flexion and extension of the knee joint, avoiding rigid collisions or excessive instantaneous force.

[0039] Specifically, the sleeve 801 is made of lightweight, high-strength plastic and has a hollow cylindrical structure. Its inner wall is smoothed to reduce frictional resistance. One end of the sleeve 801 is hinged to the middle of the first support arm 4 via a pin, forming a rotatable connection point around the pin. When the knee joint flexes and extends, the first support arm 4 moves with the lower leg, and the sleeve 801 rotates synchronously around the hinge point, always maintaining a coaxial fit with the slide rod 802, preventing misalignment or jamming of the buffer rod 8 due to the movement of the support arm. Simultaneously, the inner diameter of the hollow cavity of the sleeve 801 matches the outer diameter of the slide rod 802, providing a stable guide channel for the reciprocating sliding of the slide rod 802, ensuring that the slide rod 802 moves only axially along the sleeve 801 and does not deviate radially. The slide rod 802 has a cylindrical structure, with its outer diameter slightly smaller than the inner diameter of the sleeve 801, forming a clearance fit structure. One end of the aforementioned sliding rod 802 extends into the sleeve 801 away from the opening of the first support arm 4, and the other end is hinged to the middle of the second support arm 5 via a pin. When the knee joint is bent, the angle between the first support arm 4 and the second support arm 5 decreases, the distance between them shortens, and the sliding rod 802 slides axially inward within the sleeve 801, increasing the overlap length between the sleeve 801 and the sliding rod 802. When the knee joint is straightened, the angle between the first support arm 4 and the second support arm 5 increases, the distance between them lengthens, and the sliding rod 802 slides axially outward along the sleeve 801, decreasing the overlap length. Because the sliding rod 802 and the sleeve 801 are clearance-fitted, a small air damping is generated during the sliding process. This, combined with the vent hole 9, allows for air circulation, providing a gentle buffer for the flexion and extension of the knee joint and avoiding rigid impact caused by excessively rapid movements. Finally, the vent 9 is a circular through-hole with a diameter of 2-3 mm, located on the side wall of the sleeve 801 near the first arm 4, and penetrating both the inner and outer walls of the sleeve 801 to form an air circulation channel. When the slide rod 802 slides inside the sleeve 801, the air inside the sleeve 801 exchanges with the outside through the vent 9: when the slide rod 802 slides inward, the space inside the sleeve 801 shrinks, the air is compressed, and it is discharged through the vent 9; when the slide rod 802 slides outward, the space inside the sleeve 801 expands, and outside air enters through the vent 9 to replenish the internal air pressure. The diameter of the vent 9 is precisely designed to ensure smooth airflow to avoid excessive air resistance that could cause sliding jamming, while also enhancing the cushioning effect through appropriate air damping, making knee flexion and extension movements smoother. At the same time, the vent 9 prevents the formation of a sealed space inside the sleeve 801, which could prevent the slide rod 802 from sliding due to air pressure differences, ensuring the stable function of the buffer rod 8.

[0040] Please refer to Figure 1 , Figure 2 and Figure 6In some embodiments of this example, the first arm 4 and the second arm 5 are both provided with a fixing member 10. The fixing member 10 includes a mounting ring 1001 and an airbag 1002. The airbag 1002 is circumferentially disposed on the inner sidewall of the mounting ring 1001, and the inner sidewall of the airbag 1002 can abut against human skin.

[0041] In this embodiment, the fixing member 10 on the first arm 4 is adapted to the lower leg, and the fixing member 10 on the second arm 5 is adapted to the thigh. Both have the same structure and are fixed to the arm by the mounting ring 1001. The mounting ring 1001 serves as a basic support structure, sleeved and fixed to the inner side of the arm to ensure that the fixing member 10 and the arm form a stable whole. The airbag 1002 is distributed circumferentially along the inner wall of the mounting ring 1001, forming a ring-shaped wrap. When the patient wears the device, the first arm 4 and the second arm 5 are first placed against the outer side of the lower leg and thigh, respectively, so that the mounting ring 1001 surrounds the lower leg or thigh. Then, the airbag 1002 is inflated. After the airbag 1002 is inflated, its volume expands, and its inner wall gradually adheres to the human skin and generates moderate pressure until the arm is stably fixed to the lower leg or thigh by the support force of the airbag 1002, without obvious looseness or pressure. If it is necessary to adjust the tightness, some gas can be released through the deflation valve until a comfortable and fixed state is achieved. Furthermore, the airbag 1002 has a large contact area with the skin, which can disperse the fixed pressure over a larger area and avoid excessive local pressure. In addition, the flexible nature of the airbag 1002 allows it to deform with slight limb movements without restricting normal blood circulation, and the air chamber structure has a certain buffering effect, which can reduce the rigid pressure of the outrigger on the limb.

[0042] Please refer to Figure 6 In some embodiments of this example, the airbag 1002 is provided with an air inlet 11 for inflation or deflation, and the air inlet 11 can be connected to an inflation device.

[0043] In this embodiment, the aforementioned air nozzle 11 is integrated into the outer wall of the airbag 1002, adopting an integrated structure of a one-way valve and a detachable interface; its main body is a cylindrical interface, with a one-way sealing valve core inside and a threaded structure adapted to the inflation device on the outside; when inflation is required, the connector of the inflation device is connected and fixed to the air nozzle 11, and the inflation device is pressed or started. Gas passes through the internal channel of the air nozzle 11, opens the one-way valve core, and enters the cavity of the airbag 1002, causing the airbag 1002 to inflate; when the gas... When the pressure in the bladder 1002 reaches the expected level, inflation is stopped and the inflation device is disconnected. The one-way valve core automatically resets under the pressure inside the bladder 1002, tightly fitting the inner wall of the air nozzle 11 to block the reverse flow of gas and maintain the pressure in the bladder 1002. When it is necessary to release air to adjust the tightness, press the release button on the top of the air nozzle 11 to open the valve core and form a gas outflow channel. The gas inside the bladder 1002 is slowly discharged through the air nozzle 11 until the pressure meets the requirements. Then release the button, and the valve core resets and seals again.

[0044] Please refer to Figure 4 In some embodiments of this example, the two ends of the binding strap 1 are connected by a detachable component, which includes a Velcro 12. The Velcro 12 includes a sub-strap 1201 disposed at one end of the binding strap 1 and a mother strap 1202 disposed at the other end of the binding strap 1. The sub-strap 1201 can be attached to the mother strap 1202.

[0045] In this embodiment, the binding strap 1 is made of highly elastic and breathable fabric, and the two ends are respectively fixed with the sub-strap 1201 and the main strap 1202 of the Velcro 12: the sub-strap 1201 is a nylon strap with dense small hooks on the surface, i.e., the hook side, and is fixed to the inner side of one end of the binding strap 1; the main strap 1202 is a nylon strap with soft fiber loops on the surface, i.e., the napped side, and is fixed to the outer side of the other end of the binding strap 1, and the length of the main strap 1202 is greater than that of the sub-strap 1201.

[0046] When using the lumbar support system, the patient first places the left support 2 and right support 3 against the waist, then wraps the binding strap 1 around the waist, aligning the sub-belt 1201 with the mother belt 1202 and pressing it in place. The hooks of the sub-belt 1201 will hook onto the fiber ring of the mother belt 1202, forming a stable connection. If the tightness needs to be adjusted, the two ends of the binding strap 1 can be pulled directly to adjust the position of the sub-belt 1201 on the mother belt 1202. If disassembly is required, simply pull the two ends of the binding strap 1 in a direction perpendicular to the bonding surface to separate the hooks of the sub-belt 1201 from the fiber ring of the mother belt 1202. The entire process is tool-free and easy to operate.

[0047] Please refer to Figures 5-7 In some embodiments of this example, the first support arm 4 includes a limiting cylinder 402 and an adjusting rod 401. The adjusting rod 401 is slidably disposed inside the limiting cylinder 402. The limiting cylinder 402 is provided with a plurality of first through holes 13. The adjusting rod 401 is provided with second through holes 14 at even intervals. The central axis of any first through hole 13 may coincide with the central axis of any second through hole 14.

[0048] In this embodiment, the limiting cylinder 402 has a hollow rectangular frame structure, with one end connected to the angle limiting member 6 and the other end being an open end for the adjusting rod 401 to extend into. The adjusting rod 401 has a solid rectangular column structure, with one end extending into the open end of the limiting cylinder 402 and the other end used to install the fixing member 10. Several second through holes 14 are evenly opened along the axial direction on the side wall. The hole diameter and spacing are the same as the first through hole 13, and they are also opened on the corresponding long side wall to ensure that the first through hole 13 and the second through hole 14 can be accurately aligned when the adjusting rod 401 slides. During adjustment, the adjusting rod 401 is pushed to slide along the axial direction in the limiting cylinder 402. The rectangular cross section restricts circumferential rotation, and no additional positioning is required to prevent the rod from rotating. The central axis of the first through hole 13 and the second through hole 14 is observed and aligned, and the length is fixed by inserting the positioning pin. When disassembling, the positioning pin is pulled out, and the sliding, alignment, and pin insertion steps are repeated. No professional tools are required throughout the process.

[0049] Please refer to Figure 1 , Figure 2 and Figure 4 Both the left support 2 and the right support 3 mentioned above are adjustable telescopic structures.

[0050] In this embodiment, the left support 2 and the right support 3 are used to support the wearable mechanism. Their adjustable and telescopic structure design can flexibly adjust the length according to the waist circumference and waist contour differences of different patients, solving the problems of poor adaptability and low waist fit of traditional fixed-length supports, further improving the stability and comfort of waist wear, and providing a reliable lumbar support foundation for the entire knee fixed support training device. Example

[0051] This embodiment provides a knee training method using a knee fixation and support training device, including the following steps: S101: Based on the patient's knee injury type and rehabilitation stage, set the target buffer level of the buffer bar 8, and preset the air pressure fluctuation threshold range inside the sleeve 801 for different buffer levels. The pre-set threshold for air pressure fluctuation in the early postoperative period is 0.04-0.07×10⁻⁶. 5 Pa, recovery period is 0.05-0.08×10 5 Pa, with a functional reconstruction period of 0.08-0.10×10 5 Pa It should be noted that the target air pressure fluctuation threshold is calculated by multiplying the baseline stage coefficient by the damage correction and the body weight correction, as shown in the following formula: P = P0 × S × D × W Where P is the target air pressure fluctuation threshold; P0 is the baseline air pressure threshold during the recovery phase, specifically, in the early postoperative period: P0 = 0.05 × 10⁻⁶. 5 Pa; Recovery period: P0 = 0.08 × 10 5Pa; Functional reconstruction period: P0 = 0.12 × 10 5 Pa; S is the rehabilitation stage coefficient, D is the injury type coefficient, and W is the weight correction coefficient.

[0052] Furthermore, the above-mentioned rehabilitation stage coefficient is used to reflect the basic requirements for buffer strength at different rehabilitation stages. Strong buffering is required in the early postoperative period, and weak buffering is required in the functional reconstruction period. The calculation method in the above formula is as follows: early postoperative period: S=1.2; recovery period: S=1.0; functional reconstruction period: S=0.8. The injury type coefficients mentioned above are used to correct for differences in cushioning sensitivity among different injury types. The more severe the injury, the higher the cushioning protection required. The calculation method in the above formula is as follows: ligament rupture or postoperative repair: D=1.3; meniscus injury: D=1.1; cartilage wear or strain: D=1.0; postoperative recovery stabilization period: D=0.9; The weight correction factor mentioned above is used to adjust the air pressure threshold according to weight. The greater the weight, the higher the air pressure is required to provide sufficient support. The calculation method in the above formula is as follows: weight ≤ 40kg: W=0.85; 40kg < weight < 80kg: W=1.0; weight ≥ 80kg: W=1.15. The target air pressure fluctuation threshold is the final air pressure control range within the buffer rod 8 sleeve 801, in units of 10. 5 Pa is the upper limit of the threshold, and the lower limit is 0.4 times the upper limit by default; when = 0.1, the range is 0.04-0.1×10 5 Pa.

[0053] Calculation example: Taking a patient who weighs 90kg, has a ruptured ligament, and is in the recovery period as an example: First, determine the parameters: P0=0.08, S=1.0, D=1.3, W=1.15; Secondly, calculate the upper limit of the target air pressure: P = 0.08 × 1.0 × 1.3 × 1.15 = 0.1196 × 10 5 Pa; Final buffer level: Pressure fluctuation range of 0.0478-0.1196×10 5 Pa.

[0054] S102: A sensor installed at the pivot 602 of the angle limiting member 6 collects the relative rotational angular velocity of the first arm 4 and the second arm 5 during knee flexion and extension. At the same time, a pressure sensor installed on the inner wall of the sleeve 801 collects the dynamic air pressure value inside the sleeve 801 in real time. The first arm 4 is fixed to the lower leg and the second arm 5 is fixed to the thigh. When the knee flexes and extends, the relative rotation of the lower leg and the thigh will drive the first arm 4 and the second arm 5 to rotate, which in turn drives the pivot 602 to rotate around the base 601. When the pivot 602 rotates, the angular velocity sensor on it will detect the rotational speed of the pivot 602 in real time. This speed is directly equivalent to the relative rotational angular velocity of the first arm 4 and the second arm 5, that is, the flexion and extension rate of the knee joint. The sensor converts the detected mechanical rotation signal into electrical signals such as voltage or current and transmits them to the control unit of the device to complete the data conversion.

[0055] Furthermore, the dynamic air pressure value inside the sleeve 801 is realized through a miniature air pressure sensor embedded in the inner wall of the buffer rod 8 sleeve 801. When the knee joint flexes and extends, the relative rotation of the first arm 4 and the second arm 5 pushes the slide rod 802 to slide inside the sleeve 801. When the knee is flexed, the slide rod 802 extends into the sleeve 801, compressing the air inside the sleeve 801 and increasing the air pressure; when the knee is extended, the slide rod 802 extends out of the sleeve 801, the space inside the sleeve 801 increases, and the air pressure decreases. The air pressure sensor on the inner wall of the sleeve 801 is in direct contact with the internal air, sensing the dynamic air pressure in real time. The pressure changes are converted into corresponding electrical signals by the sensor. These signals are transmitted to the control unit and stored synchronously with the angular velocity data, forming a data set corresponding to the knee joint movement rate and the air pressure of the buffer rod 8. This data provides a basis for subsequent assessment of the buffering effect's suitability. The angular velocity data reflects the patient's actual movement speed and is used to determine if the buffering intensity needs adjustment; the air pressure data reflects the current actual buffering capacity of the buffer rod 8 and is used to verify whether the buffering intensity meets the preset threshold. Combining these two data points avoids the bias of a single data point and ensures the accuracy of subsequent buffering adjustments.

[0056] S103: The knee flexion-extension rate is calculated based on the collected relative rotational angular velocity. If the flexion-extension rate is greater than a preset threshold, it is determined that the cushioning effect needs to be enhanced; if the flexion-extension rate is less than the preset threshold, it is determined that the cushioning effect needs to be weakened. By comparing the quantified movement rate with the preset standard, the cushioning demand is dynamically judged, and the cushioning intensity is determined by the movement intensity to ensure that the knee joint is within a safe range for rehabilitation training. Specifically: The relative rotational angular velocity of the first arm 4 and the second arm 5 collected by the sensor at the pivot 602 of the angle limiter 6 is directly equivalent to the knee flexion-extension rate. The first arm 4 is fixed to the lower leg, and the second arm 5 is fixed to the thigh. The relative rotation of the two is completely synchronized with the flexion-extension movement of the knee joint. Therefore, the rotational angular velocity is the speed of the knee joint during flexion and extension. No complicated conversion is required; the real-time angular velocity value output by the sensor is the knee flexion-extension rate, which is directly used as the basis for judgment.

[0057] Furthermore, based on a preset threshold, the direction of buffering effect adjustment is determined by the relationship between the real-time rate and the threshold: the preset threshold is a safe upper limit of movement rate set in advance according to the patient's rehabilitation stage and injury type. This threshold represents the safe flexion and extension speed that the knee joint can withstand at the current stage.

[0058] When the real-time flexion-extension rate exceeds the preset threshold, it indicates that the patient's movement is too fast, and the impact force on the knee joint may exceed the safe range. At this time, it is necessary to enhance the cushioning effect by reducing the cross-sectional area of ​​the vent hole 9 of the buffer rod 8, increasing the sliding damping of the slide rod 802, and using the resistance generated by the rapid increase of air pressure inside the sleeve 801 to decelerate and reduce the impact on the joint.

[0059] When the real-time flexion-extension rate is less than the preset threshold, it indicates that the patient's movement is too slow or the cushioning is too strong, which may affect training efficiency. In this case, the cushioning effect needs to be reduced by increasing the cross-sectional area of ​​the ventilation port 9 and reducing the damping, making the slide bar 802 easier to slide, avoiding the cushioning force from becoming a resistance to movement, and ensuring the effectiveness of training.

[0060] This step is not a single determination, but is performed continuously in real time: the sensor collects angular velocity data multiple times per second, the control unit continuously compares the real-time rate with the preset threshold, and dynamically outputs instructions to strengthen or weaken the buffer. When the patient bends their knee, the rate suddenly increases from 8° / s to 12° / s, exceeding the preset threshold of 10° / s. The system immediately determines that the buffer needs to be enhanced and triggers the solenoid valve 15 on the vent 9. When the rate drops to 9° / s, it determines that the buffer needs to be weakened and the flow area of ​​the vent 9 needs to be restored.

[0061] S104: Based on the judgment result of buffering demand, adjust the airflow state of vent 9: When it is necessary to enhance buffering, control the flow rate of vent 9 through solenoid valve 15, reduce the ventilation cross-sectional area, reduce the air discharge or intake rate in sleeve 801, and increase the sliding damping of slide rod 802; when it is necessary to weaken buffering, remove the restriction of solenoid valve 15 of vent 9, so that vent 9 is in a fully open state, increase the ventilation cross-sectional area, accelerate the air flow in sleeve 801, and reduce the sliding damping of slide rod 802; by adjusting the airflow capacity of vent 9, change the air exchange rate in sleeve 801 of buffer rod 8, and then dynamically control the sliding resistance of slide rod 802 to achieve real-time adjustment of buffering effect. The damping strength is determined by airflow resistance, as follows: Buffer rod 8 is composed of sleeve 801 and slide rod 802, and the two are fitted together to form a closed air cavity.

[0062] When the knee joint is flexed and extended: When the knee is flexed, the first arm 4 and the second arm 5 bend relative to each other, the slide rod 802 is pushed into the sleeve 801, the air in the air chamber is compressed and needs to be discharged through the vent 9; when the knee is extended, the slide rod 802 is pulled out from the sleeve 801, the volume of the air chamber increases, and outside air needs to be drawn in through the vent 9. The resistance when the slide rod 802 slides directly depends on the flow speed of air through the vent 9: the slower the flow, the more drastic the change in air pressure in the air chamber, and the greater the resistance; the faster the flow, the more gradual the change in air pressure, and the smaller the resistance.

[0063] Solenoid valve 15 is a movable component installed at vent 9 and driven by the equipment control unit. It is used to change the effective flow cross-sectional area of ​​vent 9: After receiving the enhanced buffer command, the control unit drives solenoid valve 15 to operate, thereby reducing the flow rate of vent 9 and decreasing the effective flow area of ​​vent 9.

[0064] At this time, when the slide rod 802 slides, the rate at which air in the air chamber is expelled or inhaled through the vent 9 decreases: when the knee is bent to push the slide rod 802, the air is expelled slowly, the air pressure in the sleeve 801 rises rapidly, and the counter-push force on the slide rod 802 increases; when the knee is extended to pull the slide rod 802, the air is inhaled slowly, a negative pressure is formed in the sleeve 801, the pulling force on the slide rod 802 increases, the sliding of the slide rod 802 is more obviously hindered, and the buffering force received by the knee joint during flexion and extension is enhanced, avoiding the impact caused by excessively fast movements.

[0065] After receiving the reduced buffering command, the control unit drives the solenoid valve 15 to fully open the vent 9, restoring the effective flow area to its maximum. At this time, when the slide bar 802 slides, the rate of air expulsion or inhalation through the vent 9 increases: when the knee is bent and the slide bar 802 is pushed, air is quickly expelled, the air pressure inside the sleeve 801 rises slowly, and the counter-pushing force on the slide bar 802 is small; when the knee is extended and the slide bar 802 is pulled, air is quickly inhaled, the negative pressure inside the sleeve 801 is small, and the pulling force on the slide bar 802 is small. Ultimately, the slide bar 802 slides more smoothly, the buffering force on the knee joint during flexion and extension is reduced, and excessive resistance is avoided to limit normal training movements.

[0066] S105: Continuously collect the air pressure value inside the sleeve 801 and the knee flexion-extension rate, compare the real-time air pressure value with the preset air pressure fluctuation threshold. If the real-time air pressure value exceeds the threshold range, repeat step S104 to adjust the airflow state of the ventilation port 9 until the air pressure value stabilizes within the preset threshold, achieving dynamic adaptation of the buffering effect. Through the feedback mechanism of real-time monitoring, threshold comparison, and closed-loop adjustment, ensure that the actual buffering effect of the buffer rod 8 is consistent with the preset target. Using air pressure fluctuation as an indicator, the ventilation state is dynamically corrected to achieve precise adaptation of the buffering effect. Specifically: the air pressure value inside the sleeve 801 directly reflects the current damping strength of the buffer rod 8; the knee flexion-extension rate reflects the patient's movement state, and its changes will directly lead to air pressure fluctuations. The combination of the two forms a complete data chain of motion input, buffering response, and state feedback, providing a basis for adjustment.

[0067] The preset threshold is a reasonable air pressure range set according to factors such as the patient's rehabilitation stage, injury type, and weight. Essentially, the upper limit avoids excessive air pressure that could lead to overly strong cushioning and prevent the knee joint from being locked or subjected to additional pressure; the lower limit avoids insufficient air pressure that could lead to insufficient cushioning and prevent the joint from being impacted when the movement is too fast. This threshold is the baseline for judging whether the cushioning effect is up to standard.

[0068] The control unit continuously compares the real-time air pressure values ​​it collects with a preset threshold range multiple times per second. If the real-time air pressure is greater than the upper threshold: the current buffer is too strong; if the real-time air pressure is less than the lower threshold: the current buffer is too weak; if the air pressure is within the threshold: the buffer effect is deemed suitable and no adjustment is needed.

[0069] When the air pressure exceeds the threshold range, the system triggers a secondary adjustment, that is, the step S104 is repeated: If the air pressure is greater than the upper limit: control solenoid valve 15 to reduce interference with the flow of air through vent 9, accelerate air expulsion or inhalation, and reduce the air pressure inside sleeve 801 until the air pressure drops to within the threshold; if the air pressure is less than the lower limit: control solenoid valve 15 to increase interference with the flow of air through vent 9, slow down air circulation, and increase the air pressure inside sleeve 801 until the air pressure rises to within the threshold. The adjustment process is not completed in one go, but continues as the patient's movement status changes.

[0070] Furthermore, in step S101 above, the buffer level is correlated with the patient's weight. When the patient's weight is ≥80kg, the air pressure fluctuation threshold for the corresponding rehabilitation stage is increased by 15%-20%; when the patient's weight is ≤40kg, the air pressure fluctuation threshold for the corresponding rehabilitation stage is decreased by 10%-15%.

[0071] By physically linking body weight with cushioning needs, the baseline air pressure threshold is individually adjusted. Body weight determines joint load, and the load determines the cushioning intensity, ensuring that patients of different weights receive a suitable and safe cushioning effect, as detailed below: During flexion and extension exercises, the knee joint bears a portion of the patient's body weight. Differences in body weight directly lead to variations in joint load and motion inertia, fundamentally impacting the required cushioning strength: greater body weight results in greater inertia during knee movement and higher static pressure on the joint. Using a standard air pressure threshold may not provide sufficient cushioning to offset this inertial impact, potentially causing secondary joint injury. Conversely, lower body weight results in less motion inertia and lower static load on the knee joint. Using a standard air pressure threshold with excessive cushioning can restrict normal range of motion, reduce training efficiency, and even cause compensatory muscle strain. Therefore, the air pressure threshold needs to be adjusted based on body weight to match the cushioning strength with the actual load on the joint.

[0072] Specifically, based on the baseline atmospheric pressure threshold during the rehabilitation phase, percentage adjustments are made according to weight ranges, as follows: For patients weighing 80kg or more: Enhanced cushioning is necessary. Therefore, the air pressure fluctuation threshold is increased by 15%-20%. A higher air pressure threshold means a greater maximum air pressure that the sleeve 801 of the buffer rod 8 can withstand, resulting in stronger damping when the slide rod 802 slides. Increasing the threshold allows the buffer rod 8 to provide greater reaction force, counteracting the inertial impact during movement and preventing joint overload due to excessive load. For patients weighing 40kg or less: the cushioning force needs to be reduced, therefore the air pressure fluctuation threshold is lowered by 10%-15%; the lower the air pressure threshold, the smaller the maximum damping of the buffer rod 8. After lowering the threshold, the cushioning force is reduced, which can avoid restricting the joint movement of patients with low body weight due to excessive cushioning. Patients with low body weight already have low joint load, and excessive cushioning will make movement difficult and may even lead to deformed movements, affecting the rehabilitation effect; For patients with a standard weight between 40kg and 80kg: No adjustment is needed; simply use the baseline air pressure fluctuation threshold corresponding to the rehabilitation stage. Patients in this weight range have joint loads and movement inertia within the standard range, and the baseline threshold is sufficient to meet buffering needs. No additional adjustments are required to balance safety and training efficiency.

[0073] Furthermore, it also includes S106: when the air pressure value inside the sleeve 801 suddenly exceeds 0.3 × 10⁻⁶. 5 Pa or below 0.04 × 10 5When the pressure reaches 0.3 Pa, immediately control solenoid valve 15 to fully open vent 9, and simultaneously trigger a buzzer warning to prevent abnormal damping of the buffer rod 8 from impacting the knee joint. Through abnormal air pressure monitoring and emergency response mechanisms, in response to potential malfunctions or extreme movement states of the buffer rod 8, the oil worker first releases the dangerous damping, then issues a warning to minimize secondary injury to the knee joint due to abnormal damping. Specifically: when the air pressure is >0.3 × 10⁻⁶ Pa, the oil worker releases the dangerous damping and then issues a warning to minimize secondary injury to the knee joint due to abnormal damping. 5 "Pa" and "Air pressure < 0.03 × 10" 5 The "Pa" threshold is set as an emergency threshold, not randomly, but determined based on the safe working range of the buffer lever 8 and the tolerance limit of the knee joint. When air pressure > 0.3 × 10 5 Pa: At this time, the air pressure inside the sleeve 801 is too high, the damping of the buffer rod 8 will increase sharply, and the slide rod 802 will hardly be able to slide. This is equivalent to the knee joint being rigidly locked. When the patient flexes and extends, he will feel strong resistance, which may lead to muscle strain around the joint, or secondary damage to the knee cartilage and ligaments due to forced force. When the air pressure is <0.03×10 5 Pa: At this time, the air pressure inside the sleeve 801 is too low, and the buffer rod 8 has almost no damping, which is equivalent to losing the buffer protection. If the patient moves slightly faster, the knee joint will directly bear the inertia due to the lack of buffer. The above threshold is the boundary of the safe working range of the buffer rod 8. If it is exceeded, the buffer function is abnormal and emergency treatment is required.

[0074] The above description is merely a preferred embodiment of this application and is not intended to limit this application. Various modifications and variations can be made to this application by those skilled in the art. Any modifications, equivalent substitutions, improvements, etc., made within the spirit and principles of this application should be included within the protection scope of this application.

Claims

1. A knee fixation support training device, characterized in that, include: A wearable mechanism worn on the waist of a human body, the wearable mechanism includes a binding strap (1), a left support (2) and a right support (3), one end of the left support (2) is hinged to the end of the right support (3), the binding strap (1) is connected to the left support (2) and the right support (3) respectively, and the binding strap (1) is used to connect the waist of the human body; Both the left support (2) and the right support (3) are provided with a training mechanism for knee rehabilitation. Each of the training mechanisms includes a first arm (4) fixed to the lower leg and a second arm (5) fixed to the thigh. The first arm (4) and the second arm (5) are connected by an angle limiting member (6), which is used to limit the maximum bending angle of the first arm (4) and the second arm (5). A buffer element (8) is provided between the first arm (4) and the second arm (5).

2. The knee fixation and support training device according to claim 1, characterized in that, The angle limiting component (6) includes a base (601) disposed on the second arm (5), a rotating shaft (602) fixed to the first arm (4), a synchronizing block (603) and a limiting post (604). The rotating shaft (602) is rotatably disposed on the base (601). The synchronizing block (603) is disposed at the end of the rotating shaft (602) extending out of the base (601). The base (601) has several limiting slots (7) on its outer side. The limiting post (604) can extend into any of the limiting slots (7). The synchronizing block (603) can abut against the limiting post (604) under the synchronous rotation of the rotating shaft (602).

3. The knee fixation and support training device according to claim 1, characterized in that, The buffer element includes a buffer rod (8) and a solenoid valve (15) for adjusting the air intake of the buffer rod (8). The buffer rod (8) includes a sleeve (801) and a slide rod (802). One end of the sleeve (801) is hinged to the first support arm (4). One end of the slide rod (802) extends into the sleeve (801) away from the first support arm (4). The other end of the slide rod (802) is hinged to the second support arm (5). The slide rod (802) and the sleeve (801) are connected with a clearance fit. A vent hole (9) is provided on the sleeve (801). The solenoid valve (15) is provided on the vent hole (9).

4. The knee fixation and support training device according to claim 1, characterized in that, Both the first support arm (4) and the second support arm (5) are provided with a fixing member (10). The fixing member (10) includes a mounting ring (1001) and an airbag (1002). The airbag (1002) is circumferentially disposed on the inner sidewall of the mounting ring (1001). The inner sidewall of the airbag (1002) can abut against human skin.

5. The knee fixation and support training device according to claim 4, characterized in that, The airbag (1002) is provided with an air inlet (11) for inflating or deflating, and the air inlet (11) can be connected to an inflation device.

6. The knee fixation and support training device according to claim 1, characterized in that, The two ends of the binding strap (1) are connected by a detachable component, which includes a Velcro (12). The Velcro (12) includes a sub-strap (1201) disposed at one end of the binding strap (1) and a main strap (1202) disposed at the other end of the binding strap (1). The sub-strap (1201) can be attached to the main strap (1202).

7. The knee fixation and support training device according to claim 1, characterized in that, The first support arm (4) includes a limiting cylinder (402) and an adjusting rod (401). The adjusting rod (401) is slidably disposed in the limiting cylinder (402). The limiting cylinder (402) is provided with a plurality of first through holes (13). The adjusting rod (401) is provided with second through holes (14) at even intervals. The central axis of any first through hole (13) can coincide with the central axis of any second through hole (14).

8. A knee training method using a knee fixation and support training device as described in any one of claims 1 to 7, characterized in that, The method includes the following steps: S101: Based on the type of knee injury and rehabilitation stage of the patient, set the target buffer level of the buffer bar (8) and preset the air pressure fluctuation threshold range in the sleeve (801) for different buffer levels. The pre-set threshold for air pressure fluctuation in the early postoperative period is 0.04-0.07×10⁻⁶. 5 Pa, recovery period is 0.05-0.08×10 5 Pa, with a functional reconstruction period of 0.08-0.10×10 5 Pa; S102: The sensor installed at the pivot (602) of the angle limiting member (6) collects the relative rotational angular velocity of the first arm (4) and the second arm (5) during the knee flexion and extension process. At the same time, the air pressure sensor installed on the inner wall of the sleeve (801) collects the dynamic air pressure value inside the sleeve (801) in real time. S103: Calculate the knee flexion-extension rate based on the collected relative rotational angular velocity. If the flexion-extension rate is greater than the preset threshold, it is determined that the cushioning effect needs to be enhanced; if the flexion-extension rate is less than the preset threshold, it is determined that the cushioning effect needs to be weakened. S104: Based on the results of the buffering requirement judgment, adjust the airflow state of the vent (9): When the buffering needs to be enhanced, control the airflow of the vent (9) through the solenoid valve (15), reduce the airflow cross-sectional area, reduce the air discharge or intake rate in the sleeve (801), and increase the sliding damping of the slide rod (802); When the buffering needs to be weakened, control the airflow of the vent (9) through the solenoid valve (15) to increase the airflow, accelerate the airflow in the sleeve (801), and reduce the sliding damping of the slide rod (802); S105: Continuously collect the air pressure value inside the sleeve (801) and the knee flexion and extension rate, compare the real-time air pressure value with the preset air pressure fluctuation threshold. If the real-time air pressure value exceeds the threshold range, repeat step S104 to adjust the airflow state of the vent (9) until the air pressure value stabilizes within the preset threshold, so as to achieve dynamic adaptation of the buffering effect.

9. The knee training method according to claim 8, characterized in that, In step S101, the buffer level is correlated with the patient's weight. When the patient's weight is ≥80kg, the air pressure fluctuation threshold for the corresponding rehabilitation stage is increased by 15%-20%; when the patient's weight is ≤40kg, the air pressure fluctuation threshold for the corresponding rehabilitation stage is decreased by 10%-15%.

10. The knee training method according to claim 8, characterized in that, It also includes S106: when the air pressure value inside the sleeve (801) suddenly exceeds 0.3 × 10⁻⁶. 5 Pa or below 0.04 × 10 5 When Pa occurs, immediately control the solenoid valve (15) to fully open the vent (9) and trigger the buzzer alarm to avoid abnormal damping of the buffer rod (8) causing impact on the knee joint.

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