A spinal orthopedic measuring device

Abstract

This invention relates to the field of spinal orthopedics, and in particular to a spinal orthopedic measuring device. The device includes a support plate, a motor lead screw guide rail, a support arm, an electric linear module, a backrest, and a force measuring assembly. Limit switches are installed on the support plate, and the electric linear module drives the backrest to rise and fall, working in conjunction with adjustable armrests to limit the patient's posture. The motor lead screw guide rail, manual lead screw guide rail, and threaded lead screw work together to adjust the position of the force measuring sensor, accurately aligning it with the spinal measurement point. The device can accurately collect orthopedic force data and transmit it to an external system, providing experimental data for the design and production of personalized spinal orthotics. This device offers precise positioning, reliable force measurement, suitability for patients of different body types, and convenient operation, effectively improving the accuracy and efficiency of force measurement in adolescent idiopathic scoliosis orthopedics.

Description

Technical Field

[0001] This invention relates to the field of spinal orthopedics, and in particular to a spinal orthopedics measuring device. Background Technology

[0002] Adolescent idiopathic scoliosis (AIS) is a common three-dimensional spinal deformity during adolescence, characterized by insidious onset and rapid progression. Most patients experience no obvious pain or cosmetic abnormalities in the early stages, leading to a low clinical detection rate. By the time significant trunk asymmetry, uneven shoulder height, or a prominent back appear, the condition has often progressed to the middle or late stages, with a marked increase in scoliosis and a significant decrease in spinal flexibility. This means the optimal window for non-surgical correction, such as bracing and rehabilitation exercises, has been missed. In severe cases, spinal fusion surgery is required, resulting in long-term impacts on the patient's physical function, mental health, and quality of life.

[0003] Currently, in clinical practice, the determination of the magnitude, location, and direction of the orthopedic force during the customization of spinal orthopedic braces and the testing of orthopedic force largely relies on the physician's subjective experience, resulting in poor accuracy. Existing measuring devices, such as the adjustable scoliosis angle measuring bracket disclosed in Chinese utility model patent CN214104405U, only have one-dimensional height adjustment and single-angle measurement functions, failing to achieve multi-dimensional orthopedic force measurement, thus lacking accuracy and effectiveness. Furthermore, the lack of a dedicated patient posture limiting structure makes it easy for non-standard patient postures to cause force measurement point deviation. Summary of the Invention

[0004] To address the technical problems of low accuracy and poor adjustability in existing spinal detection technologies, this invention provides a spinal orthopedic measurement device.

[0005] Therefore, the present invention provides the following technical solution:

[0006] A spinal orthopedic measurement device includes a support plate. A motor lead screw guide rail is longitudinally mounted on the support plate. A support arm is mounted on the slider of the motor lead screw guide rail. A manual lead screw guide rail is horizontally mounted on the support arm. A threaded seat is mounted on the slider of the manual lead screw guide rail. A threaded lead screw is threaded onto the internal thread of the threaded seat, with the threaded lead screw perpendicular to the support plate. A force sensor is mounted on the end of the threaded lead screw facing the support plate. (The vertical height is adjusted via the motor lead screw guide rail, and the horizontal position is adjusted via the manual lead screw guide rail. This allows for multi-dimensional adjustment of the force sensor's application position, adapting to the different spinal orthopedic measurement point positioning needs of various patients. After the force position is adjusted, rotating the threaded lead screw feeds the force sensor, causing it to press against the patient for measurement.) Furthermore, a backrest is installed on the support plate, and a strip-shaped hole is opened on the backrest along the horizontal direction. Two adjustable armrests are slidably installed in the strip-shaped hole (when the patient stands sideways in front of the backrest, the two adjustable armrests on the backrest are located on the front and back sides of the patient, and the adjustable armrests are adjusted to keep the patient in an upright position).

[0007] Furthermore, the adjustable handrail is provided with a sliding rod at one end near the supporting plate. The diameter of the sliding rod is smaller than the diameter of the adjustable handrail. The sliding rod slides in the slotted hole, and a clamping nut is threaded onto the end of the sliding rod (the position of the adjustable handrail is adjusted by sliding the sliding rod in the slotted hole. After the adjustable handrail is adjusted to the position, the clamping nut is tightened to lock it in place).

[0008] Furthermore, the electric linear modules are installed longitudinally and parallel on the support plate, and the upper sliders of the electric linear modules are all installed on the same backrest; the lower sliders of the electric linear modules are all installed on the same backrest (using dual electric linear modules for synchronous drive, the backrest is raised and lowered vertically and smoothly as a whole. The upper backrest and adjustable armrest restrict the posture of the patient's upper body; the lower backrest and adjustable armrest restrict the posture of the patient's lower body, ensuring the patient's standing posture).

[0009] Furthermore, a positioning pin is fixedly installed on the slider of the electric linear module. The positioning pin has a positioning hole. A support bushing is slidably fitted on the outside of the positioning pin. The backrest plate is fixedly connected to the end of the support bushing. Adjustment holes are sequentially opened along the axial direction on the support bushing. Adjustment pins are inserted between the positioning holes and the corresponding adjustment holes (the backrest plate is adjusted in the forward and backward distance by sliding the support bushing relative to the positioning pin. The positioning holes and adjustment holes are locked by the alignment pins to achieve precise positioning of the backrest).

[0010] Furthermore, a pull rod is installed on the adjusting pin (the adjusting pin can be easily inserted and removed via the pull rod, facilitating quick and easy switching of the support bushing and positioning pin positions, making operation labor-saving and convenient).

[0011] Furthermore, the support bushing is provided with a compression spring inside, which abuts against the end of the adjusting pin (after the adjusting pin is pulled out, the compression spring can restore the support bushing and the positioning pin to their initial positions, facilitating the next adjustment).

[0012] Furthermore, an upper limit switch and a lower limit switch are installed on the support plate. The upper limit switch and the lower limit switch correspond to the upper limit position and the lower limit position of the motor lead screw guide slider, respectively (to limit the upper and lower travel of the motor lead screw guide slider).

[0013] Furthermore, a handwheel is installed at the end of the threaded screw away from the support plate (rotating the handwheel drives the threaded screw to extend and retract axially, and the manual fine-tuning operation is intuitive and has high control precision; the number of rotations of the handwheel can be used to obtain the movement distance of the threaded screw).

[0014] Furthermore, a side cover is installed on the support plate, and the motor lead screw guide rail is located inside the side cover; a base is installed at the bottom of the support plate, and an anti-slip plate is installed on the upper side of the base (the side cover provides dust protection, safety isolation and security for the motor lead screw guide rail; the base provides stable support for the whole machine, and the anti-slip plate increases the friction of the contact surface to prevent patients from slipping).

[0015] Advantages and positive effects of the present invention: The force sensor height is adjusted via a motor-driven lead screw guide, while its horizontal position is finely adjusted via a manual lead screw guide. Once adjusted, the force sensor is aligned with the measurement point on the spine via a handwheel-driven screw feed, enabling three-dimensional position adjustment. The force sensor then collects spinal orthopedic force parameters with high precision. The backrest height is adjusted via an electric linear module to accommodate patients of different heights, while the sliding armrests accommodate patients of different body types, ensuring that patients maintain a standard upright posture. This further improves the authenticity and accuracy of the force measurement data, providing precise measured data for subsequent orthopedic device design. Attached Figure Description

[0016] To more clearly illustrate the technical solutions in the embodiments of the present invention 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 some embodiments of the present invention. For those skilled in the art, other drawings can be obtained based on these drawings without creative effort.

[0017] Figure 1 This is a schematic diagram of the main structure of the support plate of a spinal orthopedic measuring device provided by the present invention.

[0018] Figure 2 This is a front view structural diagram of a spinal orthopedic measurement device provided by the present invention.

[0019] Figure 3 This is a side view structural diagram of a spinal orthopedic measurement device provided by the present invention.

[0020] Figure 4 This is a top view schematic diagram of a spinal orthopedic measurement device provided by the present invention.

[0021] Figure 5 This is a top view of the backrest structure of a spinal orthopedic measurement device provided by the present invention.

[0022] In the diagram: 1. Support plate; 2. Motor lead screw guide rail; 3. Support arm; 4. Base; 5. Anti-slip plate; 6. Side cover; 7. Electric linear module; 8. Backrest panel; 9. Manual lead screw guide rail; 10. Threaded seat; 11. Threaded lead screw; 12. Handwheel; 13. Adjustable armrest; 14. Sliding rod; 15. Clamping nut; 16. Positioning pin; 17. Positioning hole; 18. Support bushing; 19. Adjustment hole; 20. Adjustment pin; 21. Pull rod; 22. Compression spring. Detailed Implementation

[0023] To enable those skilled in the art to better understand the present invention, the technical solutions of the present invention will be clearly and completely described below with reference to the accompanying drawings of the embodiments of the present invention. Obviously, the described embodiments are only some embodiments of the present invention, and not all embodiments. Based on the embodiments of the present invention, all other embodiments obtained by those skilled in the art without creative effort should fall within the scope of protection of the present invention.

[0024] This invention provides a spinal orthopedic measurement device, such as... Figure 1-4 As shown, the system includes a support plate 1, on which a motor lead screw guide rail 2 is longitudinally mounted. An upper limit switch and a lower limit switch are also mounted on the support plate 1, corresponding to the upper and lower limit positions of the slider of the motor lead screw guide rail 2, respectively. A support arm 3 is mounted on the slider of the motor lead screw guide rail 2, and a manual lead screw guide rail 9 is horizontally mounted on the support arm 3. A threaded seat 10 is mounted on the slider of the manual lead screw guide rail 9, and a threaded lead screw 11 is threaded onto the internal thread of the threaded seat 10, with the threaded lead screw 11 perpendicularly facing the support plate 1. A force sensor is mounted on the end of the threaded lead screw 11 facing the support plate 1. A handwheel 12 is mounted on the end of the threaded lead screw 11 away from the support plate 1.

[0025] The electric linear modules 7 are longitudinally and parallelly mounted on the support plate 1. The upper sliders of the electric linear modules 7 are all mounted on the same backrest plate 8; the lower sliders of the electric linear modules 7 are also all mounted on the same backrest plate 8. Specifically, as shown... Figure 5 As shown, a positioning pin 16 is fixedly installed on the slider of the electric linear module 7. The positioning pin 16 has a positioning hole 17. A support bushing 18 is slidably fitted onto the outside of the positioning pin 16. The backrest plate 8 is fixedly connected to the end of the support bushing 18. Adjustment holes 19 are sequentially formed along the axial direction on the support bushing 18. Adjustment pins 20 are inserted between the positioning hole 17 and the corresponding adjustment hole 19. A pull rod 21 is installed on the adjustment pin 20. A compression spring 22 is provided inside the support bushing 18, and the compression spring 22 abuts against the end of the adjustment pin 20.

[0026] The backrest panel 8 has a horizontally oriented strip hole, within which two adjustable armrests 13 are slidably installed. Specifically, one end of the adjustable armrest 13 near the supporting upright plate 1 has a sliding rod 14. The diameter of the sliding rod 14 is smaller than the diameter of the adjustable armrest 13. The sliding rod 14 is slidably installed in the strip hole, and a clamping nut 15 is threaded onto the end of the sliding rod 14.

[0027] A side cover 6 is installed on the support plate 1, and the motor lead screw guide rail 2 is located inside the side cover 6; a base 4 is installed at the bottom of the support plate 1, and an anti-slip plate 5 is installed on the upper side of the base 4.

[0028] Working principle: After the patient is in position, the overall height of the backrest 8 is adjusted using the electric linear module 7, and the front-to-back distance of the backrest 8 is adjusted by the cooperation of the positioning pin 16, the support bushing 18, the adjusting pin 20 and the compression spring 22. Then, the adjustable armrest 13 is slidable through the strip hole on the backrest 8, and locked by the sliding rod 14 and the clamping nut 15 to limit and straighten the patient's torso, maintaining a standard upright testing posture.

[0029] The motor lead screw guide rail 2 on the support plate 1 drives the support arm 3 to move vertically. The upper and lower limit switches limit the safe stroke of the slider, achieving coarse adjustment of the force measuring point height. Then, the manual lead screw guide rail 9 on the support arm 3 drives the threaded seat 10 for horizontal fine adjustment, accurately aligning the force sensor at the end of the threaded screw 11 with the part of the patient's spine to be measured. Rotating the handwheel 12 drives the threaded screw 11 to feed axially, allowing the force sensor to smoothly press against the human spine, and collecting the actual orthopedic force parameters in real time. When the patient's spinal Cobb angle reaches 0° or reaches the patient's pain tolerance limit, the measured actual orthopedic force is the rated orthopedic force.

[0030] The entire machine is stable with the base 4 and anti-slip plate 5, and the side cover 6 provides dust protection for the motor lead screw guide rail 2.

[0031] The pressure signal collected by the force sensor is processed by internal A / D conversion and calculation, and the measured orthopedic force, rated orthopedic force, measuring point position, and jacking displacement data are transmitted to the external design system. After receiving the measured data, the external system performs simulation modeling and mechanical matching in combination with the patient's spinal deformity parameters. Based on the real measured data, it completes the digital design of the personalized spinal orthosis structural parameters and finally outputs the model and processing parameters, which are directly used for the customized design and manufacturing of the spinal orthosis.

[0032] Example 1 Currently, the core of conservative treatment for AIS in clinical practice is the wearing of spinal orthoses. However, existing spinal orthoses have many technical shortcomings in design and application, making it difficult to meet the needs of precise correction and dynamic control in the early stages of the disease. In the orthodontic design stage, traditional methods rely heavily on physician experience for manual modeling, lacking scientific quantitative basis. They fail to establish a precise correlation between Cobb angle, patient BMI, and orthodontic force and displacement, resulting in low accuracy of digital modeling. The support curvature and orthodontic force of the orthodontic device do not match the individual spinal deformity characteristics of the patient, easily leading to problems such as poor fit and unsatisfactory orthodontic effect. In fact, excessive or insufficient orthodontic force may even aggravate spinal injury.

[0033] To address the technical problem of low accuracy in digital modeling caused by the lack of a precise correlation between Cobb angle, patient BMI, and corrective force and displacement in existing technologies, a spinal orthosis is designed using the device described in this application, including the following steps: S1. Have the patient stand in the force measurement area of ​​the force measuring device and complete the body posture limit. Rotate the threaded screw of the force measuring device to feed the threaded screw towards the patient's test area and apply an increasing corrective force to the patient. Record the displacement of the apical vertebra and the real-time corrective force. Define the displacement corresponding to when the scoliosis is corrected to the Cobb angle of 0° or when the patient's pain reaches the limit of tolerance as the rated displacement and the corresponding corrective force as the rated corrective force. Establish a measured database of corrective force-displacement.

[0034] S2. Collect patient height and weight data to calculate BMI index, take a full-spine anteroposterior X-ray of the patient, and extract the patient's Cobb angle and apical vertebra position as body geometry parameters. The apical vertebra position is the vertebral segment within the scoliosis arc that is furthest from the midline of the human trunk and has the greatest degree of vertebral rotation.

[0035] S3. Based on the patient's measured data, the nonlinear quadratic function relationships of Cobb angle-rated orthopedic force, BMI-rated orthopedic force, and rated orthopedic force-rated displacement were obtained.

[0036] S4. Substitute the patient's BMI and Cobb angle into the corresponding nonlinear quadratic function to calculate the patient's appropriate rated orthopedic force and rated displacement of the apical region.

[0037] S5. Input the human body circumference parameters, Cobb angle, apical vertebra position, rated orthopedic force, and rated displacement into Solidworks modeling software. Use the modeling software to construct a basic framework that matches the patient's torso. After spline curve lofting and solid thickening, a preliminary three-dimensional model of the orthosis is obtained. The preliminary three-dimensional model of the orthosis is then topologically optimized to remove redundant materials that do not support the orthopedic area, resulting in the final three-dimensional model of the orthosis.

[0038] Topology optimization employs a variable density method for iterative calculation, with maximum stiffness as the objective and a volume fraction ≤ 65% as the constraint. The penalty factor p ranges from 2 to 5, and the number of iterations ranges from 50 to 200. Specifically, the penalty factor p = 3, and the number of iterations is 80.

[0039] The force application area of ​​the three-dimensional model of the orthosis is set according to the position of the apex vertebra. The indentation distance of the force application area into the orthosis is the calculated rated displacement. The resultant force is the resultant force of the lateral convexity correction push force and the vertebral anti-rotation force.

[0040] S6. Import the 3D model of the orthodont into the 3D printing equipment, using PLA-PCL copolymer for integral molding. The layer thickness is 0.05~0.3mm, the nozzle temperature is 190~230℃, the heated bed temperature is 45~60℃, and the printing speed is 40~80mm / s to complete the solid molding. Specifically, the layer thickness is 0.2mm, the nozzle temperature is 210℃, the heated bed temperature is 60℃, and the printing speed is 60mm / s.

[0041] Ming uses a spinal orthopedic measuring device to collect force and displacement data of the patient's apical vertebrae on-site. At the same time, it combines the Cobb angle and the human body's pain tolerance limit to define the rated orthopedic force and rated displacement. The parameters are close to the patient's actual body stress state, which effectively avoids the problems of excessive orthopedic force causing body compression injury and insufficient orthopedic force failing to achieve the corrective effect, thus improving the safety and effectiveness of the treatment.

[0042] Through experimental testing, a stable nonlinear quadratic function relationship was established between the Cobb angle, patient BMI, rated orthopedic force, and rated displacement. This allowed for the mechanical quantification of the orthotic design process, avoiding the problem of insufficient precision caused by traditional orthotic designs relying solely on the physician's subjective experience.

[0043] The BMI index can be calculated based on different patient body types. The Cobb angle of scoliosis and the position of the apex vertebra can be extracted by combining spinal X-ray images. The parameters can be quickly calculated by fitting the fitting function to determine the corrective mechanical parameters specific to the patient. This determines the force application point, indentation distance and resultant force of the orthosis, so that the structure and force distribution of the orthosis are highly consistent with the patient's spinal deformity characteristics, greatly improving the fit and correction accuracy.

[0044] By incorporating both the geometric parameters of spinal deformity and the measured mechanical parameters into the 3D modeling process, and moving away from solely relying on external dimensions for modeling, the overall accuracy of digital modeling is effectively improved.

[0045] Example 2 Most existing conventional orthotics only have passive shaping and correction functions, and cannot monitor the actual orthodontic force under different body postures during daily wear in real time. Medical staff have difficulty accurately grasping the patient's actual wearing status, effective correction time, and the effect of the applied corrective force. They cannot detect abnormalities such as excessive or insufficient orthodontic force or improper wearing in time, and cannot achieve dynamic adjustment of the correction plan. As a result, the orthodontic effect is difficult to guarantee, and it is also easy to cause physical discomfort due to improper force, delaying the best time for correction. Overall, there are significant limitations in clinical use and precise correction effect.

[0046] To address the technical problem that existing orthotics cannot monitor the actual orthopedic force under different body postures during daily wear, thus preventing dynamic adjustment of the correction plan, a spinal orthotics designed using the device in this application is used to monitor the patient's orthopedic status.

[0047] The spinal orthosis designed using the device described in this application includes an orthosis body, a battery, an analog-to-digital converter (ADC), and a controller. The orthosis body has a non-enclosed structure and is equipped with straps for wearing and securing. Pressure sensors are installed in the force application area inside the orthosis body, and the force application area corresponds to the position of the patient's apical vertebra. The signal output terminal of the pressure sensor is connected to the signal input terminal of the ADC, and the signal output terminal of the ADC is connected to the signal input terminal of the controller. The ADC and controller are both located on the outside of the orthosis body, and the power terminals of the pressure sensor, ADC, and controller are all electrically connected to the battery. The signal output terminal of the controller is connected to the cloud platform of an external smart terminal.

[0048] The pressure sensor is a thin-film pressure sensor, characterized by its thinness, softness, and conformability to the human body surface. It can fit closely to the inside of the orthosis and make close contact with the patient's body without affecting daily limb activities. It can accurately sense the compressive force on the apical region. The battery is a flexible lithium film battery, which is soft and can be installed on the outer wall of the orthosis. It occupies little space, adapts to the wearing shape of the orthosis, and can provide stable power for a long time to meet the needs of all-weather wearable monitoring. The controller is an ESP32 controller, which integrates wireless communication functions and can stably complete data processing and wireless signal transmission and reception. The analog-to-digital converter is a 16-bit ADC, which can accurately acquire the weak analog electrical signals output by the pressure sensor, improve the accuracy of pressure value acquisition, and reduce data acquisition errors.

[0049] The orthosis is fitted with a protective shell on the outside, and the analog-to-digital converter and controller are located inside the protective shell to avoid bumps and knocks during daily wear.

[0050] Monitoring using this spinal orthosis includes the following steps: S1. Measure the rated orthopedic force required for spinal correction using an orthopedic force measuring device, and record the rated orthopedic force value in the cloud platform of an external smart terminal; before formal monitoring, medical staff first use a dedicated force measuring device to determine the rated orthopedic force suitable for the patient based on the degree of scoliosis and body characteristics, and complete the filing and storage of basic correction parameters.

[0051] S2. Manufacture a spinal orthosis based on the patient's body parameters and rated orthopedic force; combine the patient's height, body circumference, spinal deformity location and the calculated rated orthopedic force to customize and process a spinal orthosis of the corresponding specifications, ensuring that the overall shape of the orthosis fits the patient's back curve and the force application point is accurately aligned with the correction position of the top vertebra of the spine.

[0052] S3. The patient wears a spinal orthosis, and the actual orthopedic force applied to the patient by the spinal orthosis is monitored in real time by pressure sensors. The patient wears the orthosis neatly against the back and completes the wearing and fixation by the outer strap of the main body. After the orthosis is worn, the pressure sensors installed on the inner side can collect the actual compression force on the correction area around the clock, realizing dynamic data collection at all times.

[0053] S4. The actual orthopedic force is converted into a digital signal by an analog-to-digital converter and transmitted to the controller. The controller then transmits the digital signal to the cloud platform of the external smart terminal. The continuous analog pressure signal collected by the pressure sensor is converted into a digital signal that can be recognized and read by the controller through an analog-to-digital converter. The controller then transmits the real-time orthopedic force data wirelessly to the smart terminal held by the patient. Finally, the data is aggregated and uploaded to the backend cloud platform for unified data storage.

[0054] The S5 cloud platform compares the actual orthopedic force with the rated orthopedic force, and evaluates the spinal correction effect under the patient's standing posture and in the state of wearing the device at all times.

[0055] When the patient is standing, the orthopedic effect is rated as excellent when the actual orthopedic force is 90% to 105% of the rated orthopedic force; good when the actual orthopedic force is 75% to 90% of the rated orthopedic force; effective when the actual orthopedic force is 50% to 75% of the rated orthopedic force; and ineffective when the actual orthopedic force is less than 50% of the rated orthopedic force.

[0056] When the actual orthopedic force exceeds 105% of the rated orthopedic force, the smart terminal issues an alert, reminding the patient to loosen the bandage; when the actual orthopedic force is less than 50% of the rated orthopedic force, the smart terminal issues an alert, reminding the patient to tighten the bandage.

[0057] When the patient is in any posture other than standing, the orthopedic effect is considered effective when the actual orthopedic force is 0-30% of the rated orthopedic force.

[0058] The orthotic force measured by the pressure sensor is the highest when the patient is standing and the lowest when the patient is lying down. When the orthotic force measured by the pressure sensor fluctuates between the maximum and minimum values, it indicates that the patient's position has changed and the orthosis is working normally. When the orthosis is in a continuously ineffective state for more than 12 hours, the smart terminal issues an early warning to remind the patient to tighten the straps.

[0059] S6. When the assessment result is invalid, the smart terminal issues an alert, reminding the patient to adjust the orthotic straps until the orthotic effect is assessed as effective. After receiving the abnormal force warning, the patient can independently fine-tune the tightness of the straps, changing the corrective force applied by the orthotic in real time until the monitoring data returns to the effective range.

[0060] Example: Setting the baseline: Patient A, aged 14, was wearing and fitting a pressure sensor orthosis for the first time. The doctor had the patient stand still and measured the maximum orthotic force (rated orthotic force).

[0061] Account binding: The doctor generates a unique invitation code on the web interface. Patient A's guardian enters the code into a mini-program on an external smart terminal to complete the registration, and the two systems are successfully bound together.

[0062] It needs to be worn for approximately 22 hours each day. In the evening, the guardian turns on the Bluetooth of their smart device, accesses the mini-program, connects to the orthotics controller via Bluetooth, and uploads the day's orthotics force data to the cloud.

[0063] Static (standing) real-time monitoring: On Saturday morning, when patient A was standing, the caregiver viewed the real-time orthopedic force via a mini-program. Excellent: 95% of rated force (between 90% and 105%). System evaluation is excellent; continue to maintain this level.

[0064] Excessive force: exceeding 105%. The doctor suggested via a mini-program: Please loosen the restraints appropriately to prevent pressure sores.

[0065] The force is too low: between 50% and 75%. Doctor's advice: Please tighten the bandage to improve the effect.

[0066] Failure: Excluding cases where the garment was not worn, this indicates a design failure, and the system prompts the user to seek immediate medical attention for replacement.

[0067] The comprehensive 24-hour dynamic assessment takes into account that patient A's force may decrease during dynamic activities such as walking and sleeping. The system uses >30% of rated force as the effective working state and calculates the percentage of effective time per day:

[0068] Finally, it should be noted that the above embodiments are only used to illustrate the technical solutions of the present invention, and not to limit them. 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 or all of the technical features therein. Such modifications or substitutions do not cause the essence of the corresponding technical solutions to deviate from the scope of the technical solutions of the embodiments of the present invention.

Claims

1. A spinal orthopedic measuring device, characterized in that, The system includes a support plate (1), on which a motor lead screw guide rail (2) is mounted longitudinally. A support arm (3) is mounted on the slider of the motor lead screw guide rail (2). A manual lead screw guide rail (9) is mounted horizontally on the support arm (3). A threaded seat (10) is mounted on the slider of the manual lead screw guide rail (9). A threaded lead screw (11) is mounted on the internal thread of the threaded seat (10). The threaded lead screw (11) is perpendicular to the support plate (1). A force sensor is mounted on the end of the threaded lead screw (11) facing the support plate (1).

2. The spinal orthopedic measuring device according to claim 1, characterized in that, A backrest plate (8) is installed on the support plate (1). A strip hole is opened on the backrest plate (8) along the horizontal direction, and two adjustable armrests (13) are slidably installed in the strip hole.

3. The spinal orthopedic measuring device according to claim 2, characterized in that, The adjustable handrail (13) has a sliding rod (14) at one end near the support plate (1). The diameter of the sliding rod (14) is smaller than the diameter of the adjustable handrail (13). The sliding rod (14) is slidably installed in the strip hole. The end of the sliding rod (14) is threaded with a clamping nut (15).

4. The spinal orthopedic measuring device according to claim 2, characterized in that, The electric linear module (7) is installed longitudinally and parallel on the support plate (1). The upper sliders of the electric linear module (7) are all installed on the same backrest plate (8). The lower sliders of the electric linear module (7) are all installed on the same backrest plate (8).

5. A spinal orthopedic measuring device according to claim 4, characterized in that, The electric linear module (7) has a fixedly installed positioning pin (16) on its slider. The positioning pin (16) has a positioning hole (17) and a support bushing (18) is slidably fitted on the outside of the positioning pin (16). The backrest plate (8) is fixedly connected to the end of the support bushing (18). The support bushing (18) has adjustment holes (19) sequentially opened along the axial direction. An adjustment pin (20) is inserted between the positioning hole (17) and the corresponding adjustment hole (19).

6. A spinal orthopedic measuring device according to claim 5, characterized in that, A pull rod (21) is installed on the adjusting pin (20).

7. A spinal orthopedic measuring device according to claim 5, characterized in that, The support bushing (18) is provided with a compression spring (22), which abuts against the end of the adjusting pin (20).

8. A spinal orthopedic measuring device according to claim 1, characterized in that, The upper limit switch and the lower limit switch are installed on the support plate (1). The upper limit switch and the lower limit switch correspond to the upper limit position and the lower limit position of the slider of the motor screw guide rail (2), respectively.

9. A spinal orthopedic measuring device according to claim 1, characterized in that, A handwheel (12) is installed at the end of the threaded rod (11) away from the support plate (1).

10. A spinal orthopedic measuring device according to claim 1, characterized in that, Side cover (6) is installed on the support plate (1), and motor screw guide rail (2) is located inside the side cover (6); base (4) is installed at the bottom of the support plate (1), and anti-slip plate (5) is installed on the upper side of the base (4).

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