Scoliosis dynamic air pressure correction device and method adaptive to respiratory movement

Abstract

The invention discloses a scoliosis dynamic air pressure correction device and method matched with respiratory movement, and relates to the technical field of medical instruments. The device comprises a multi-cavity air bag assembly, a double-sensing module, a respiration-air pressure matching calculation module and a precise air pressure adjusting module, two-dimensional data collection is achieved through an air bag built-in pressure sensor and a thoracic strain sensor, and air pressure fluctuation caused by respiratory movement is counteracted in real time by combining the reverse dynamic adjusting logic of inspiration pressure reduction and expiration pressure increase; and the deviation of the correction force is controlled within + / -2kPa. The orthodontic brace solves the problem that the orthodontic force of a traditional brace is overloaded or insufficient due to breathing, personalized correction can be achieved on the basis of the Cobb angle and breathing characteristics of a patient, the response time is adjusted to be smaller than or equal to 0.1 second, the orthodontic brace has the characteristics of low noise, antibiosis, overpressure protection and the like, the scoliosis correction effect and wearing comfort are remarkably improved, and the orthodontic brace is suitable for teenagers and adults with the Cobb angle of 10-40 degrees.

Description

Technical Field

[0001] This invention relates to the field of medical device technology, specifically to a dynamic pneumatic correction device and method for conservative treatment of scoliosis, particularly suitable for airbag-type correction scenarios where it is clamped between an external brace frame and the lateral aspect of the thoracic cavity. It can counteract the fluctuations in corrective force caused by respiratory movements in real time. While improving the accuracy of scoliosis correction, it also enhances the comfort of the wearer, providing a better solution for conservative treatment of scoliosis in adolescents and adults. Background Technology

[0002] Scoliosis, a common spinal deformity among adolescents, is often treated with braces, which are the preferred clinical option in conservative treatment due to their core function of applying a constant corrective force to the curved vertebrae and guiding the spine back to its normal physiological curvature. While the currently mainstream pneumatic braces offer advantages in terms of flexibility and fit, they suffer from three major drawbacks in practical application, severely limiting their corrective effectiveness and patient tolerance:

[0003] (1) Poor stability of corrective force: When the airbag is clamped between the external brace frame and the outer side of the thorax, respiratory movements will directly cause passive changes in the airbag pressure. During inhalation, the thorax expands outward and compresses the airbag, causing the airbag pressure to rise sharply, and the corrective force exceeds the target value by 15%-30%, which can easily damage the local soft tissues of the thorax, hinder blood circulation, and even lead to the risk of overcorrection; during exhalation, the thorax contracts inward and increases the space that the airbag can accommodate, and the air pressure drops accordingly, and the corrective force is reduced by 20%-40% compared with the target value, which cannot effectively maintain the corrective effect on the scoliosis vertebrae and weaken the treatment effect.

[0004] (2) Lack of personalized adaptation: There are significant differences in the degree of scoliosis (e.g., Cobb angle 10°-40°), respiratory rate (12-20 breaths / minute for adolescents, 8-16 breaths / minute for adults), and chest expansion (individual differences of 3-8 mm) among different individuals. Existing devices do not calibrate the degree of adjustment according to individual respiratory characteristics and scoliosis parameters, and adopt a uniform "one-size-fits-all" adjustment logic, which leads to over-adjustment (e.g., low Cobb angle individuals experience excessive corrective force) or under-adjustment (e.g., high Cobb angle individuals experience insufficient corrective force) in some individuals, and cannot adapt to diverse correction needs.

[0005] (3) Lagging adjustment response: Some dynamic adjustment schemes rely solely on a single chest deformation sensor (such as an infrared ranging sensor) to indirectly infer changes in airbag pressure, without directly collecting actual airbag pressure data. This leads to a disconnect between the adjustment logic and the actual airbag pressure state. Data transmission delays generally exceed 0.3 seconds, and adjustment response delays often exceed 0.5 seconds. This makes it impossible to follow the breathing rhythm (0.8-5 seconds per respiratory cycle) in real time to correct the corrective force, creating a vicious cycle of "adjustment lagging behind respiratory changes". Summary of the Invention

[0006] This invention aims to solve the problem of fluctuations in corrective force caused by respiratory movements in existing scoliosis airbag correction devices, specifically addressing the following core technical issues:

[0007] ① During the inhalation phase, the pressure of the airbag increases and the corrective force is overloaded. During the exhalation phase, the airbag relaxes and the pressure decreases and the corrective force is insufficient, which in turn leads to the risk of pressure injury and weakened corrective effect.

[0008] ② The adjustment logic does not take into account the individual's breathing characteristics (breathing rate, chest expansion range) and lateral curvature parameters (Cobb angle), which makes it impossible to achieve personalized correction and results in poor adaptability;

[0009] ③ The regulatory response is lagging, and it cannot adjust the air pressure in real time to keep up with the breathing rhythm, resulting in the problem of the corrective force being out of sync with the breathing movement.

[0010] To achieve the above objectives, the present invention provides a dynamic pneumatic correction device for scoliosis that adapts to respiratory movements. The device consists of a brace frame, a multi-chamber airbag, a dual-sensor module, a breathing-pressure matching calculation module, and a precise pressure regulation module. The modules work together to achieve the reverse dynamic regulation logic of "inhalation lowering pressure and exhalation raising pressure".

[0011] A dynamic pneumatic correction device for scoliosis adapted to respiratory movements. The device's support frame comprises an upper support ring 9, a middle support ring 8, a lower support ring 4, a support back plate 10, a support cross plate 11, and support side posts 12, all fixed by locking screws.

[0012] A dynamic pneumatic correction device for scoliosis adapted to respiratory movements. The device is characterized by a multi-chamber airbag consisting of a convex main airbag 7, a concave upper auxiliary airbag 1, and a concave lower auxiliary airbag 3. The convex main airbag 7 is fixed to the middle ring 8 of the brace using Velcro or clips; the concave upper auxiliary airbag 1 is fixed to the upper ring 9 of the brace using Velcro or clips; and the concave lower auxiliary airbag 3 is fixed to the lower ring 4 of the brace using Velcro or clips.

[0013] A dynamic pneumatic correction device for scoliosis adapted to respiratory movements. The device's dual-sensor module consists of three miniature absolute pressure sensors 13 embedded in airbags, one thoracic strain sensor 5, and a dual-sensor module circuit box 6. The thoracic strain sensor 5 is attached to the location of the most significant chest expansion using medical low-sensitivity adhesive. The dual-sensor module circuit box 6 contains a data acquisition circuit, a Bluetooth 5.3 low-power module, and a battery. The miniature absolute pressure sensors 13 and the thoracic strain sensor 5 are connected to the dual-sensor module circuit box 6 via cables.

[0014] A dynamic pneumatic correction device for scoliosis adapted to respiratory movements. The device is characterized by a breathing-pressure matching calculation module 17 with a built-in circuit board, battery, and Bluetooth 5.3 low-power module, installed inside a central control circuit box 2. The breathing-pressure matching calculation module 17 is connected to a touchscreen 18 to view and modify control parameters.

[0015] A dynamic pneumatic correction device for scoliosis adapted to respiratory movements. The device is characterized by a precision pneumatic adjustment module comprising three sets of miniature air pumps 15 and miniature air valves 16. Each set of air pumps and valves is connected via an air tube 14 to the convex-side main airbag 7 and the concave-side upper auxiliary airbag 1 and concave-side lower auxiliary airbag 3 for inflation and deflation control. The precision pneumatic adjustment module is connected to a breathing-pressure matching calculation module 17 via a control signal line.

[0016] A dynamic pneumatic correction device for scoliosis adapted to respiratory movements. Its key feature is that each module works in concert to achieve a reverse dynamic adjustment logic of "inhalation reducing pressure, exhalation increasing pressure," with the specific structure and function as follows:

[0017] ① Multi-chamber airbag

[0018] Installation and positioning: It is clamped between the external brace frame (such as the thoracolumbar brace frame) and the outer side of the human chest, and fixed by Velcro or buckles to ensure that the convex side main airbag 7 is aligned with the convex side vertebral body area of ​​the scoliosis, and the concave side upper auxiliary airbag 1 and concave side lower auxiliary airbag 3 are symmetrically attached to the concave side vertebral body area to achieve targeted correction.

[0019] Chamber structure: It adopts a "1 main and 2 auxiliary" independent chamber design, including a convex side main airbag 7, a concave side upper auxiliary airbag 1, and a concave side lower auxiliary airbag 3. Each chamber is independently separated and the air pressure can be adjusted separately to adapt to different correction needs of lateral curvature convex and concave sides.

[0020] Material characteristics: Medical-grade polyurethane elastic material is selected, with a thickness controlled between 0.3-0.5mm. After fatigue testing, the deformation recovery rate is ≥50% after 5000 inflation and deflation cycles, avoiding elasticity decay caused by long-term wear; the surface is sprayed with an antibacterial coating (such as silver ion coating), with an antibacterial rate of ≥99%, reducing the risk of skin infection.

[0021] ② Dual-sensing module

[0022] Miniature absolute pressure sensor 13: Convex side main airbag 7, concave side upper auxiliary airbag 1, concave side lower auxiliary airbag 3. Each airbag chamber is embedded with a miniature absolute pressure sensor 13, with a measurement range of 0-100kPa, an accuracy of ±1kPa, a sampling frequency of 10Hz, and real-time acquisition of the actual air pressure value of each chamber, directly feeding back the corrective force status.

[0023] Thoracic strain sensor 5: It adopts a flexible strain gauge and is attached to the position where the human chest expands most significantly (such as the 6th-8th ribs under the armpit, the 4th-5th ribs beside the sternum) with medical low-sensitivity adhesive. It measures deformation range of 0-20mm and accuracy of ±0.1mm. The respiratory stage is judged by the deformation change rate (deformation increases during inhalation and decreases during exhalation).

[0024] Data transmission: It adopts a Bluetooth 5.3 low power module with a transmission rate of ≥2Mbps and a transmission latency of ≤0.05 seconds. It can work stably in environments ranging from -10℃ to 40℃, making it suitable for daily wear scenarios, while reducing power consumption (single charge battery life ≥72 hours).

[0025] ③ Breathing-Pressure Matching Calculation Module 17

[0026] Hardware carrier: The core control unit is an STM32L431 microcontroller with a main frequency of 80MHz. It has low power consumption characteristics (standby current ≤10μA, operating current ≤5mA) and is equipped with 128KB Flash memory and 32KB RAM, which can store one month of air pressure regulation data.

[0027] Core functions:

[0028] a. Personalized Target Calibration: The system receives human parameters (age, height, Cobb angle 10°-40°) input by the doctor via a touchscreen. Based on a built-in algorithm, it automatically matches the target air pressure for each airbag chamber: when the Cobb angle is 10°-20°, the convex main airbag is 720-22 kPa, the upper concave auxiliary airbag 1 and the lower concave auxiliary airbag 3 are 18-19 kPa; when the Cobb angle is 20°-30°, the convex main airbag is 723-25 ​​kPa, the upper concave auxiliary airbag 1 and the lower concave auxiliary airbag 3 are 19-20 kPa; when the Cobb angle is 30°-40°, the convex main airbag is 726-28 kPa, the upper concave auxiliary airbag 1 and the lower concave auxiliary airbag 3 are 21-22 kPa. The target values ​​are then stored as adjustment benchmarks.

[0029] b. Real-time deviation calculation: Every 0.05 seconds, the actual air pressure collected by the miniature absolute pressure sensor 13 is compared with the target air pressure. When the deviation is > ±2kPa, an adjustment command is triggered: During the inhalation phase, if the actual air pressure is > the target air pressure, the "amount of air pressure to be released = actual air pressure - target air pressure" is calculated; during the exhalation phase, if the actual air pressure is < the target air pressure, the "amount of air pressure to be replenished = target air pressure - actual air pressure" is calculated.

[0030] c. Breathing intensity adaptation: Based on the chest deformation amplitude collected by the strain sensor, "calm breathing" (deformation amplitude < 5 mm) and "deep breathing" (deformation amplitude ≥ 5 mm) are distinguished, and the adjustment amplitude is adjusted accordingly: the adjustment amount is 80% of the calculated value during calm breathing to avoid over-adjustment; the adjustment amount is 120% of the calculated value during deep breathing to ensure sufficient corrective force. At the same time, the breathing rate is recorded, and when the frequency fluctuation exceeds ±3 breaths / minute, the adjustment response speed is automatically fine-tuned.

[0031] ④ Precision air pressure regulation module

[0032] Miniature air valve 16: Convex side main airbag 7, concave side upper auxiliary airbag 1, concave side lower auxiliary airbag 3. Each airbag chamber is equipped with one miniature air valve 16 with a diameter of 0.2-0.5mm, a response time of ≤0.1 seconds, and an operating voltage of 3.3V. During the inhalation phase, it receives the "pressure reduction command" from the calculation module, accurately exhausts air according to the "required air pressure", receives feedback data from the miniature absolute pressure sensor 13 in real time, and immediately closes after the air pressure reaches the standard, with a closing leakage of ≤0.1mL / min.

[0033] Miniature air pump 15: Convex side main airbag 7, concave side upper auxiliary airbag 1, concave side lower auxiliary airbag 3. Each airbag chamber is equipped with a diaphragm-type miniature air pump. The diaphragm-type miniature air pump has an operating voltage of 5V, a rated air pressure of 100kPa, a flow rate of 50-100mL / min, and a noise level of ≤35dB. The diaphragm-type miniature air pump is connected to the convex side main airbag 7, the concave side upper auxiliary airbag 1, and the concave side lower auxiliary airbag 3 respectively through one-way valves. During the exhalation phase, it receives the "pressure boosting command" and replenishes air according to the "required air pressure amount". It stops operating after the air pressure reaches the target value.

[0034] Safety protection mechanism: Built-in overpressure protection unit. When the actual air pressure of the convex side main airbag 7, the concave side upper auxiliary airbag 1, and the concave side lower auxiliary airbag 3 exceeds 50% of the target air pressure (e.g., when the target is 25 kPa, the actual pressure is ≥37.5 kPa), emergency exhaust will be automatically triggered until the air pressure drops to below 120% of the target air pressure. At the same time, low battery protection is set. When the battery power is <10%, the minimum safe air pressure (15 kPa) will be automatically maintained and an alarm will be issued.

[0035] (3) Correction methods

[0036] Based on the above-mentioned device, the present invention also provides a dynamic pneumatic correction method for scoliosis adapted to respiratory movements, which includes the following three core steps:

[0037] Step 1: Personalized parameter calibration (performed upon first wear, takes approximately 15 minutes)

[0038] 1. The human body wears a brace frame. Medical staff fix the multi-chamber airbag between the outer side of the thoracic cavity and the brace frame for positioning, ensuring that the main airbag 7 on the convex side is aligned with the center of the convex vertebral body on the scoliosis, and the upper auxiliary airbag 1 and the lower auxiliary airbag 3 on the concave side are symmetrically attached to the concave vertebral body.

[0039] 2. Doctors input human information (age, height, weight, Cobb angle) through the human-computer interaction interface: touch screen 18. The system automatically generates the initial target air pressure values ​​for each air chamber of the convex side main airbag 7, the concave side upper auxiliary airbag 1, and the concave side lower auxiliary airbag 3, and displays them on the touch screen 18.

[0040] 3. Guide the human body to complete 5 calm breaths (each breathing cycle lasts 3-5 seconds) and 3 deep breaths (each breathing cycle lasts 5-8 seconds). The system records in real time the maximum air pressure deviation of each chamber of the convex side main air bladder 7, the concave side upper auxiliary air bladder 1, and the concave side lower auxiliary air bladder 3 during inhalation, and the minimum air pressure deviation during exhalation. Based on the deviation data, the system automatically corrects the adjustment amplitude parameters (such as the calm breathing adjustment coefficient and the deep breathing adjustment coefficient) to complete personalized calibration. The calibration data is automatically stored in the local memory.

[0041] Step 2: Dynamic correction adjustment (performed in real time during daily wear)

[0042] 1. The dual sensing module collects the actual air pressure value of the airbag and the chest deformation data at a frequency of 0.05 seconds / time, and transmits them to the breathing-pressure matching calculation module 17 via Bluetooth 5.3 low power module;

[0043] 2. The calculation module analyzes data in real time: If the chest cavity size shows an increasing trend (determined to be in the inhalation stage), and the actual air pressure of the convex side main airbag 7, the concave side upper auxiliary airbag 1, and the concave side lower auxiliary airbag 3 is greater than the target air pressure + 2kPa, a "pressure reduction command" is immediately sent to the micro air valve 16 of the corresponding airbag, controlling the micro air valve 16 to release air according to "the amount of air pressure to be released × the breathing intensity coefficient" until the air pressure drops to within the target air pressure ± 2kPa range, and then the exhaust valve is closed;

[0044] 3. If the chest cavity size shows a decreasing trend (determined to be in the expiratory phase), and the actual air pressure of the convex main air bladder 7, the concave upper auxiliary air bladder 1, and the concave lower auxiliary air bladder 3 is less than the target air pressure - 2 kPa, a "pressure boosting command" is sent to the micro air pump 15, controlling the micro air pump 15 to replenish air according to "required replenishment air pressure × breathing intensity coefficient" until the air pressure reaches the target air pressure.

[0045] Within the ±2kPa range, stop the air pump operation;

[0046] 4. During the adjustment process, the miniature absolute pressure sensor 13 continuously feeds back air pressure data, and the calculation module dynamically corrects the adjustment amount every 0.01 seconds to ensure that the adjustment deviation is always ≤±2kPa, thereby achieving real-time dynamic correction that follows the breathing rhythm.

[0047] Step 3: Data monitoring and optimization (performed periodically)

[0048] 1. The breathing-pressure matching calculation module 17 automatically generates a "Corrective Force Stability Report" every week, which includes data such as the average daily pressure deviation, the maximum deviation during deep breathing, the number of daily adjustments, and the trend of respiratory rate changes. It can be synchronized to the doctor's terminal (such as a computer or tablet) via Bluetooth.

[0049] 2. The doctor assesses the corrective effect based on the report: If the daily deviation is > ±1.5kPa, the target air pressure value is adjusted (minor adjustment of ±2kPa every two weeks); if the local air pressure deviation is too large, the airbag installation position is checked and repositioned; if the body reports discomfort, the breathing intensity coefficient is optimized to continuously improve the corrective effect and wearing comfort.

[0050] (4) Beneficial effects

[0051] Compared with existing scoliosis airbag correction technology, the present invention has the following significant advantages:

[0052] 1. Precise and stable corrective force: Through the reverse dynamic adjustment logic of "inhalation to reduce pressure and exhalation to increase pressure", combined with the real-time data acquisition of the dual sensing module, the fluctuation range of corrective force is reduced from ±15kPa of traditional devices to within ±2kPa, effectively avoiding the problems of overload pressure injury during inhalation and undercorrection during exhalation, and improving the stability of the corrective effect.

[0053] 2. Strong personalized adaptability: Based on the human Cobb angle, respiratory rate, and chest expansion amplitude, the target air pressure and adjustment parameters are calibrated, breaking the "one-size-fits-all" adjustment mode. It can adapt to people with Cobb angles of 10°-40° and different age groups, meeting diverse correction needs.

[0054] 3. Timely response and comfortable to wear: The dual sensing module has a transmission delay of ≤0.05 seconds and an adjustment module response time of ≤0.1 seconds. It can adjust the air pressure in real time according to the breathing rhythm (0.8-5 seconds per breathing cycle) to avoid adjustment lag; the micro air pump 15 (noise ≤35 decibels) and elastic airbag material (deformation recovery rate ≥50%) reduce noise interference and foreign body sensation when wearing, and improve the human body's long-term wear tolerance;

[0055] 4. High safety: Built-in overpressure protection (automatic exhaust when the target air pressure exceeds 50%), low power protection (maintains safe air pressure when the power is low) and antibacterial coating (antibacterial rate ≥99%) triple safety mechanism, effectively avoids tissue damage caused by abnormal air pressure, correction interruption caused by insufficient power and skin infection risk, and ensures long-term wear safety. Attached Figure Description

[0056] Figure 1 Overall structural diagram of a dynamic pneumatic correction device for scoliosis adapted to respiratory movements.

[0057] Figure 1 middle:

[0058] 1 is the concave upper accessory airbag

[0059] 2 is the central control circuit box

[0060] 3 is the concave lower accessory airbag

[0061] 4 is the lower ring of the brace.

[0062] 5 is a thoracic strain sensor

[0063] 6 is a dual-sensing module circuit box

[0064] 7 is the main airbag on the convex side.

[0065] 8 is the middle ring of the support.

[0066] 9 is the upper ring of the brace.

[0067] 10 is the back plate of the brace.

[0068] 11 is a cross-shaped support plate.

[0069] 12 is the side column of the support.

[0070] Figure 2 Cross-sectional structure diagram of the airbag

[0071] Figure 2 middle

[0072] 13 is a miniature absolute pressure sensor

[0073] 14 is the trachea

[0074] Figure 3 Internal diagram of the central control circuit box

[0075] Figure 3 middle

[0076] 15 is a miniature air pump

[0077] 16-bit miniature air valve

[0078] 17 is the breathing-pressure matching calculation module.

[0079] Figure 4 Human-computer interaction interface (touchscreen)

[0080] Figure 4 middle

[0081] 18-bit touchscreen Detailed Implementation

[0082] To make the technical solution of the present invention clearer and easier to understand, the apparatus and method of the present invention will be further described in detail below with reference to specific embodiments. The embodiments are only used to explain the present invention and do not constitute a limitation on the scope of protection.

[0083] Example 1: A 14-year-old adolescent (165cm tall, 50kg) with a Cobb angle of 25°.

[0084] ① Device parameter calibration

[0085] 1. The human body's Cobb angle is 25°. The system automatically matches the target air pressure based on the built-in algorithm: convex side main airbag 7: 25 kPa, concave side upper auxiliary airbag 1 and concave side lower auxiliary airbag 3 are both 20 kPa;

[0086] 2. The normal breathing rate is 18 breaths / minute, and the chest expansion is 4mm (normal breathing) and 8mm (deep breathing). The system sets the breathing intensity coefficient as follows: 80% of the calculated deviation value during normal breathing and 120% during deep breathing.

[0087] 3. During the calibration process, the human body completes 5 calm breaths and 3 deep breaths. The system records the maximum air pressure deviation of the convex side main airbag 7 during inhalation (+3.2 kPa) and the minimum air pressure deviation during exhalation (-2.8 kPa), and automatically corrects and adjusts the parameters to complete the calibration.

[0088] ②Dynamic adjustment process

[0089] 1. Calm breathing - Inhalation phase: The chest deformation amplitude is 4mm, and the actual air pressure of the convex side main airbag 7 rises to 28kPa (deviation +3kPa > ±2kPa). The calculation module triggers the "pressure reduction command". The amount of air pressure to be released is 28kPa - 25kPa = 3kPa, and the adjustment amount is 3kPa × 80% = 2.4kPa. The micro air valve 16 opens, releasing 2.4kPa of air pressure. The air pressure of the convex side main airbag 7 drops to 25.6kPa (deviation +0.6kPa ≤ ±2kPa), and the micro air valve 16 closes.

[0090] 2. Calm breathing - exhalation phase: The chest contracts, and the actual air pressure in the convex side main airbag 7 drops to 22 kPa (deviation -3 kPa < ±2 kPa). The calculation module triggers a "pressure boosting command". The required air pressure is 25 kPa - 22 kPa = 3 kPa, and the adjustment amount is 3 kPa × 80% = 2.4 kPa. The micro air pump 15 starts, supplementing 2.4 kPa of air pressure. The air pressure in the convex side main airbag 7 rises to 24.4 kPa (deviation -0.6 kPa ≤ ±2 kPa), and the micro air pump 15 stops.

[0091] 3. Deep breathing - Inhalation phase: The chest deformation amplitude is 8mm, the actual air pressure of the convex side main airbag 7 rises to 31kPa (deviation +6kPa>±2kPa), the required air pressure release = 31kPa - 25kPa = 6kPa, the adjustment amount = 6kPa × 120% = 7.2kPa; the micro air valve 16 opens, releasing 7.2kPa of air pressure, the air pressure of the convex side main airbag 7 drops to 23.8kPa (deviation -1.2kPa≤±2kPa), and the micro air valve 16 closes;

[0092] 4. Deep breathing - exhalation phase: The chest cavity contracts significantly, and the actual air pressure of the convex side main air bag 7 drops to 20 kPa (deviation -5 kPa < ±2 kPa). The required air pressure is 25 kPa - 20 kPa = 5 kPa, and the adjustment amount is 5 kPa × 120% = 6 kPa. The micro air pump 15 starts, supplementing 6 kPa of air pressure, and the air pressure of the convex side main air bag 7 rises to 26 kPa (deviation +1 kPa ≤ ±2 kPa). The micro air pump 15 then stops.

[0093] ③Effect Verification

[0094] 1. After 7 days of continuous wear, the system recorded an average daily air pressure deviation of ±1.5 kPa, with the maximum deviation observed during deep breathing.

[0095] ±1.8kPa, all controlled within ±2kPa, the stability of the corrective force is significantly better than that of traditional devices;

[0096] 2. Human feedback: There was no chest compression or stuffiness during wear. The noise of the miniature air pump at night did not affect sleep (ambient noise level was 32 decibels). The wearability was good.

[0097] 3.2-week follow-up examination: X-ray measurement showed that the Cobb angle of the human body decreased from 25° to 23°, the correction effect was stable, and there were no signs of damage such as redness, swelling or tenderness in the local soft tissue of the chest, which verified the effectiveness and safety of the invention.

Claims

1. A dynamic pneumatic correction device for scoliosis adapted to respiratory movements, characterized in that, It includes a multi-chamber airbag assembly, a dual-sensor module, a breathing-pressure matching calculation module, and a precise pressure regulation module; the multi-chamber airbag consists of a convex main airbag, a concave upper auxiliary airbag, and a concave lower auxiliary airbag. The convex main airbag is fixed to the middle ring of the brace using Velcro or buckles, the concave upper auxiliary airbag is fixed to the upper ring of the brace using Velcro or buckles, and the concave lower auxiliary airbag is fixed to the lower ring of the brace using Velcro or buckles. The dual-sensing module consists of a miniature absolute pressure sensor, a thoracic strain sensor, and a dual-sensing module circuit box. The thoracic strain sensor is attached to the position of the human thoracic expansion most obviously using medical low-sensitivity adhesive. The dual-sensing module circuit box has a built-in acquisition circuit, a Bluetooth module, and a battery. The miniature absolute pressure sensor and the thoracic strain sensor are connected to the dual-sensing module circuit box via cables. Miniature absolute pressure sensors collect the actual air pressure values ​​of each chamber, and thoracic strain sensors collect thoracic deformation data to determine the breathing stage. The sensors and flexible strain gauges transmit data to the breathing-pressure matching calculation module via Bluetooth, with a transmission delay of ≤0.05 seconds. The breathing-pressure matching calculation module receives the human body's lateral bending parameters and automatically matches the target pressure of each airbag chamber. It compares the actual pressure with the calculated deviation of the target pressure, combines the chest deformation data to distinguish the breathing intensity, and generates the adjustment command of "inhalation to lower pressure, exhalation to raise pressure". The precise air pressure regulation module includes an electromagnetic exhaust valve corresponding to each airbag chamber and a low-noise micro air pump connected to each chamber. It receives regulation commands to achieve precise release or replenishment of air pressure, with a regulation response time of ≤0.1 seconds.

2. The apparatus according to claim 1, characterized in that, The sensor model is MS5803-14BA, with a measurement range of 0-100kPa and an accuracy of ±1kPa; the flexible strain gauge model is KFGS-2-120-C1-11 L3M2R, with a deformation detection range of 0-20mm and an accuracy of ±0.1mm.

3. The apparatus according to claim 1, characterized in that, The respiratory-barometry matching calculation module incorporates a personalized calibration algorithm to automatically match target barometry for patients with a Cobb angle of 10°-40°: Cobb angle 10°-20°. When the Cobb angle is 20°-30°, the main cavity on the convex side has a pressure of 20-22 kPa and the secondary cavity on the concave side has a pressure of 18-19 kPa; when the Cobb angle is 30°-40°, the main cavity on the convex side has a pressure of 23-25 ​​kPa and the secondary cavity on the concave side has a pressure of 19-20 kPa; when the Cobb angle is 30°-40°, the main cavity on the convex side has a pressure of 26-28 kPa and the secondary cavity on the concave side has a pressure of 21-22 kPa.

4. The apparatus according to claim 1, characterized in that, The breathing-pressure matching calculation module has a breathing intensity adaptation function: when the chest deformation amplitude is <5mm, it is determined to be calm breathing, and the adjustment amount is 80% of the calculated pressure deviation value; when the chest deformation amplitude is ≥5mm, it is determined to be deep breathing, and the adjustment amount is 120% of the calculated pressure deviation value.

5. The apparatus according to claim 1, characterized in that, The high-speed electromagnetic exhaust valve is model SV01-2P025-06, with a response time ≤0.1 seconds, a diameter of 0.2-0.5 mm, and a closing leakage rate ≤0.1 mL / min; the low-noise micro air pump is model PM3005, with a noise level ≤35 decibels, a rated air pressure of 100 kPa, and a flow rate of 50-100 mL / min.

6. The apparatus according to claim 1, characterized in that, The precise air pressure regulation module also includes an overpressure protection unit: when the actual air pressure of the airbag exceeds 50% of the target air pressure, it automatically triggers emergency venting until the air pressure drops below 120% of the target air pressure; at the same time, it is equipped with a low battery protection unit, which maintains a minimum safe air pressure of 15kPa and alarms when the battery power is <10%.

7. The apparatus according to claim 1, characterized in that, The multi-chamber airbag assembly is made of medical-grade polyurethane elastic material with a thickness of 0.3-0.5mm and a deformation recovery rate of ≥50%. The surface is coated with a silver ion antibacterial coating with an antibacterial rate of ≥99%. Each chamber is equipped with a one-way pressure relief valve.

8. A dynamic pneumatic correction method for scoliosis adapted to respiratory movements, based on the device described in any one of claims 1-7, characterized in that, Includes the following steps: S1: Personalized parameter calibration: Fix the multi-chamber airbag assembly between the outer side of the thoracic cage and the external brace frame, input the human body Cobb angle and respiratory rate parameters, and the patient completes 5 calm breaths and 3 deep breaths. The system automatically calibrates the target air pressure and respiratory intensity adaptation parameters for each chamber. S2: Dynamic correction and adjustment: The dual sensing module collects the actual air pressure of the airbag and the chest deformation data in real time, and the calculation module judges the breathing stage: If the actual air pressure is greater than the target air pressure +2kPa during inhalation, the exhaust valve is controlled to reduce the pressure by the adjustment amount; if the actual air pressure is less than the target air pressure -2kPa during exhalation, the air pump is controlled to increase the pressure by the adjustment amount to ensure that the air pressure deviation is ≤±2kPa. S3: Data Monitoring and Optimization: A weekly "Corrective Force Stability Report" is generated. The target air pressure or airbag installation position is adjusted according to the report. The target air pressure is fine-tuned by ±2kPa every 2 weeks to optimize the correction effect.

9. The method according to claim 8, characterized in that, In step S1, the personalized parameter calibration takes 15 minutes. The system automatically corrects the breathing intensity adaptation parameters by recording the maximum air pressure deviation of each chamber during inhalation and the minimum air pressure deviation during exhalation.

10. The method according to claim 8, characterized in that, In step S2, the data acquisition frequency of the dual-sensor module is 10Hz, and the calculation module dynamically corrects the adjustment amount every 0.01 seconds, with an adjustment response time of ≤0.1 seconds, thereby achieving real-time synchronization of breathing rhythm and air pressure regulation.

Images