Athletic rehabilitation auxiliary wearable equipment suitable for diabetics and obese patients

Abstract

The invention relates to the field of rehabilitation medical treatment, in particular to exercise rehabilitation auxiliary wearable equipment suitable for diabetics and obese patients, which comprises a single chip microcomputer and a plantar pressure adjusting assembly, the plantar pressure adjusting assembly comprises an insole, a plurality of openings are formed in the insole, and a plurality of elastic membranes used for sealing the openings are fixedly connected to the top of the insole; the insole is provided with a sensing assembly used for monitoring plantar pressure, and the sensing assembly is located below the elastic membrane and is in signal connection with the single-chip microcomputer. The bottom of the insole is fixedly connected with a substrate layer, a plurality of air cavities are formed in the substrate layer, and the air cavities are communicated with the adjacent openings; folding assemblies used for enhancing the supporting rigidity of the elastic membranes are arranged in the air cavities. By collecting plantar pressure data and regulating and controlling the supporting rigidity of the elastic membrane and the folding assembly, dynamic adaptation of the plantar supporting rigidity is achieved, the risks of foot ulcers of diabetic patients and plantar strain of obese patients are reduced, and comfort and safety in the exercise rehabilitation process are improved.

Description

Technical Field

[0001] This invention relates to the field of rehabilitation medicine, specifically to a wearable assistive device for exercise rehabilitation suitable for patients with diabetes and obesity. Background Technology

[0002] Diabetic patients need to avoid drastic fluctuations in blood sugar, while obese patients need to efficiently control their energy intake and lose fat; both must balance the safety and sustainability of their exercise. Wearable sports rehabilitation devices can monitor key data such as heart rate and exercise intensity in real time, preventing sudden spikes and drops in blood sugar caused by blind exercise. Through data visualization, patients can clearly see the effectiveness of their exercise, helping them establish regular exercise habits, ultimately reducing the risk of complications and improving rehabilitation efficiency and quality of life.

[0003] Currently, wearable assistive devices for sports rehabilitation have been applied to some extent in the field of rehabilitation medicine. Existing products mainly include ordinary orthotic insoles, simple pressure monitoring shoes, and upper limb rehabilitation training bracelets. Among them, ordinary orthotic insoles are mostly made of elastic materials with fixed hardness. They adapt to specific foot shapes through preset support structures and are placed directly inside the shoe, relying on the elasticity of the material itself to provide basic cushioning. Simple pressure monitoring shoes usually embed discrete pressure sensors in key parts of the insole. After connecting to an external data acquisition terminal, they can display local pressure data of the sole in real time. Users need to adjust their walking posture or change to insoles with different hardness through the terminal readings. Upper limb rehabilitation training bracelets integrate sensors such as accelerometers to assist patients in upper limb function recovery training by monitoring limb movement trajectories.

[0004] Diabetic patients often suffer from peripheral neuropathy, leading to a loss of protective sensation in the feet and an inability to detect abnormal pressure stimuli in a timely manner. Abnormal plantar pressure distribution is a major contributing factor to serious complications such as foot ulcers. However, existing wearable rehabilitation devices primarily focus on upper limb or trunk rehabilitation, with a lack of dedicated foot-specific devices. Among the few foot-related devices available, ordinary orthotic insoles only provide fixed support and cannot respond to dynamic pressure changes in real time. While simple pressure monitoring shoes can collect pressure data, they only display the data and cannot adjust stiffness according to real-time pressure changes during walking, failing to fundamentally address the injury problems caused by abnormal foot pressure. Therefore, there is an urgent need for a wearable rehabilitation device suitable for diabetic and obese patients to solve these problems. Summary of the Invention

[0005] To address the aforementioned issues, this invention provides a wearable exercise rehabilitation aid suitable for diabetic and obese patients. By collecting plantar pressure data, it adjusts the support stiffness of elastic diaphragms and folding components to achieve dynamic adaptation of support stiffness in different areas of the foot during walking, thereby dispersing local pressure hotspots and reducing the risk of foot ulcers in diabetic patients and plantar strain in obese patients.

[0006] To achieve the above objectives, the technical solution of the present invention is as follows: A wearable assistive device for exercise rehabilitation suitable for diabetic and obese patients, comprising a microcontroller and a plantar pressure adjustment component; the plantar pressure adjustment component includes an insole, on which several openings are formed, and several elastic diaphragms for closing the openings are fixedly connected to the top of the insole; a sensing component for monitoring plantar pressure is provided on the insole, the sensing component is located below the elastic diaphragms and is signal-connected to the microcontroller; a base layer is fixedly connected to the bottom of the insole, and several air chambers are formed in the base layer, each air chamber communicating with its adjacent opening; each air chamber is provided with a folding component for enhancing the support stiffness of the elastic diaphragms; an installation groove is formed at the heel of the base layer, and a pump component is provided in the installation groove, the pump component being electrically connected to the microcontroller, the output end of the pump component being connected to an air guide tube, the other end of the air guide tube being connected to each air chamber, the air guide tube being used to deliver gas into the air chamber to deform the elastic diaphragms and adjust the support stiffness of the insole; a first solenoid valve is connected to each connection between the air chamber and the air guide tube, and the first solenoid valve is electrically connected to the microcontroller.

[0007] The technical principles of the above solution are as follows:

[0008] When the elastic diaphragm is subjected to pressure from the sole of the foot, it deforms, triggering the sensing component to collect pressure data of the foot zones and transmit it to the microcontroller. After analyzing the data, the microcontroller sends a command to the pump assembly in the mounting slot and the first solenoid valve of the corresponding air chamber. The compressed gas generated by the pump assembly is delivered to the target air chamber through the air guide tube, pushing the elastic diaphragm to bulge upward to increase the support stiffness. At the same time, the folding component in the air chamber expands or contracts with changes in air pressure, assisting the elastic diaphragm to strengthen the support or return to its initial state. By regulating the air pressure, dynamic regulation of the plantar pressure is achieved.

[0009] The above approach has the following beneficial effects:

[0010] 1. This solution uses real-time pressure data from the sensing components to pneumatically adjust the support stiffness of different areas of the foot, achieving dynamic adaptation of support stiffness in different areas of the sole, thus reducing the risk of foot ulcers in diabetic patients and foot strain in obese patients.

[0011] 2. The air chamber in this solution, in conjunction with the corresponding sensing and folding components, enables independent adjustment of a single area. Compared to the overall support adjustment of traditional equipment, it can solve the problem of excessive local pressure, effectively disperse foot pressure, and improve the comfort and effectiveness of sports rehabilitation.

[0012] 3. This solution uses a microcontroller to directly convert pressure data into mechanical intervention, improving the intelligence and practicality of the equipment and ensuring the safety of exercise rehabilitation for diabetic and obese patients.

[0013] Furthermore, the openings are located at the forefoot, arch, and heel of the insole. Specifically, the openings at the forefoot correspond to the big toe ball, the second and third toe balls, and the fourth and fifth toe balls, respectively; the openings at the arch correspond to the medial and lateral arches, respectively; and the openings at the heel correspond to the medial and lateral sides of the heel, respectively.

[0014] Beneficial effects: The opening is set independently according to the anatomical divisions of the forefoot, arch, and heel to adapt to the physiological structure and motion force characteristics of different areas of the human foot, so as to achieve subsequent zoned control of pressure.

[0015] Furthermore, the sensing component includes several sets of flexible pressure sensor arrays, which are used to monitor foot pressure and transmit pressure signals to the microcontroller; each set of flexible pressure sensor arrays is arranged in an equilateral triangle along the circumference of the opening, and all flexible pressure sensor arrays are located below the elastic diaphragm and are fixedly connected to the insole.

[0016] Beneficial effects: The flexible pressure sensor array is arranged in an equilateral triangle along the circumference of the opening, which can capture the deformation signal of the elastic diaphragm after being subjected to foot pressure from all directions. Compared with traditional single-point or linear pressure sensing methods, it can improve the accuracy and coverage of foot zone pressure monitoring.

[0017] Furthermore, the folding assembly includes an airbag, which is fixedly connected to the side wall of the air chamber. An "N"-shaped elastic support piece is fixedly connected inside the airbag, which folds the airbag into an "N" shape in the initial state. Several auxiliary air tubes are connected to the air guide tube, and the other end of each auxiliary air tube is connected to an adjacent airbag. A second solenoid valve is connected at the connection between the auxiliary air tube and the air guide tube, and the second solenoid valve is electrically connected to a single-chip microcomputer. The gaps between the two sides of the airbag and the side wall of the air chamber form a channel.

[0018] Beneficial effects: The airbag achieves graded adjustment of support stiffness through the folding and inflation of the N-shaped elastic support plate, while the channel ensures airflow between the air chamber and the air tube, avoiding excessive local air pressure.

[0019] Furthermore, the airbag contains ball bearings, which are initially positioned at the lowest point of the folded "N"-shaped elastic support sheet. Several ejector pins are slidably fitted onto the inner wall of the base layer, with one end of each pin extending into the adjacent airbag and positioned at the top of the elastic support sheet along with the ball bearings. Several through slots are formed within the base layer, and each through slot is fixedly connected to a varistor, which is electrically connected to a single-chip microcomputer. The other end of each ejector pin extends into the adjacent through slot and contacts the varistor.

[0020] Beneficial effects: By using the displacement of the ball bearings in conjunction with the expansion or contraction of the air bladder to compress the pressure-sensitive resistor, it is possible not only to monitor the degree of expansion of the elastic support plate and the actual support force inside the air bladder, but also to provide a secondary verification basis for the pressure data of the microcontroller.

[0021] Furthermore, a partition is fixedly connected inside the mounting slot, which divides the mounting slot into a control chamber and an adjustment chamber. The pump assembly is located inside the adjustment chamber, and shock-absorbing foam is fixedly connected inside the adjustment chamber.

[0022] Beneficial effects: The partition divides the mounting slot into independent control chamber and adjustment chamber, avoiding interference from the components in the control chamber caused by the vibration and airflow disturbance of the pump assembly during operation; at the same time, the shock-absorbing foam in the adjustment chamber fits tightly against the pump assembly, which can effectively absorb the vibration and noise generated by the operation of the pump assembly, preventing the vibration from being transmitted to the insole and affecting the patient's exercise comfort, and also cushioning the impact of repeated pressure from the heel on the pump assembly.

[0023] Furthermore, the control cavity is equipped with a posture sensing component, which includes a MEMS integrated chip. The axis of the MEMS integrated chip is coaxially mounted with the foot movement trajectory. The MEMS integrated chip has a built-in three-axis accelerometer and a three-axis gyroscope. The three-axis accelerometer is used to collect the acceleration changes of the foot in three-dimensional space and convert them into motion intensity, cadence, and stride length data. The three-axis gyroscope is used to collect the angular velocity changes of the foot around the three-dimensional axis. The MEMS integrated chip transmits the motion intensity, cadence, stride length data, and angular velocity change data to the microcontroller.

[0024] Beneficial effects: By combining MEMS integrated chips with triaxial accelerometers and triaxial gyroscopes, real-time data on the three-dimensional acceleration and angular velocity changes of the feet can be collected and converted into data on motion intensity, step frequency, stride length, and angular velocity changes, which are then transmitted to the microcontroller, providing a basis for the microcontroller to optimize the adjustment of support stiffness.

[0025] Furthermore, it also includes a physiological signal acquisition component and a blood glucose intelligent regulation system; the physiological signal acquisition component is used to collect heart rate variability data, skin conductance response data and CGM blood glucose change data, and transmit the heart rate variability data, skin conductance response data and CGM blood glucose change data to the blood glucose intelligent regulation system.

[0026] Beneficial effects: The physiological signal acquisition component can collect and transmit physiological indicators such as heart rate variability, skin conductance response and CGM blood glucose changes in real time, providing physiological data support for the intelligent blood glucose regulation system under exercise conditions.

[0027] Furthermore, the intelligent blood glucose control system is connected to a microcontroller. The intelligent blood glucose control system includes a multi-signal preprocessing module and a blood glucose trend prediction model. The multi-signal preprocessing module is used to perform noise reduction and standardization on heart rate variability data, skin conductance response data, CGM blood glucose change data, exercise intensity, cadence, stride length data, and angular velocity change data, and extract feature parameters. The blood glucose trend prediction model is used to train an LSTM neural network model based on massive amounts of heart rate variability data, skin conductance response data, and CGM blood glucose change data in patient exercise scenarios, and learn the leading correlation between heart rate variability data, skin conductance response data, exercise intensity, and blood glucose changes 5-15 minutes later.

[0028] Beneficial effects: By using a multi-signal preprocessing module to denoise and standardize physiological and exercise data and extract feature parameters, and then using an LSTM neural network model to obtain the advanced correlation between heart rate variability, skin conductance response, exercise intensity and blood glucose changes 5-15 minutes later, the trend of blood glucose changes during exercise can be predicted in advance to a certain extent.

[0029] Furthermore, the intelligent blood glucose regulation system also includes a multivariate intervention module. This module integrates CGM blood glucose change data, in vivo insulin dosage, carbohydrate intake, and exercise intensity data. It simulates intervention measures through a multivariate linear regression model and outputs suggestions to stabilize blood glucose within a safe range.

[0030] Beneficial effects: By integrating CGM blood glucose change data, in vivo insulin dosage, carbohydrate intake and exercise intensity data, and using a multivariate linear regression model to simulate the regulatory effects of different intervention measures, suggestions are provided to stabilize blood glucose within a safe range, thus achieving blood glucose regulation in exercise scenarios. Attached Figure Description

[0031] Figure 1 This is an isometric view of an embodiment of the sports rehabilitation assistive wearable device for diabetic and obese patients according to the present invention.

[0032] Figure 2 This is an isometric sectional view of an embodiment of the sports rehabilitation assistive wearable device for diabetic and obese patients of the present invention.

[0033] Figure 3 For the present invention Figure 2 Enlarged view of part A in the middle.

[0034] Figure 4 This is a partial cross-sectional view of an embodiment of the sports rehabilitation assistive wearable device of the present invention applicable to patients with diabetes and obesity.

[0035] Figure 5 For the present invention Figure 4The enlarged view of section B shows the direction of gas flow indicated by the dashed arrows.

[0036] Figure 6 This is a cross-sectional view of the base layer of an embodiment of the wearable sports rehabilitation aid for patients with diabetes and obesity according to the present invention.

[0037] Figure 7 This is a top view of the insole of an embodiment of the sports rehabilitation assistive wearable device for diabetic and obese patients according to the present invention.

[0038] Figure 8 This is a top view of the air chamber of an embodiment of the wearable sports rehabilitation aid for diabetic and obese patients of the present invention.

[0039] The reference numerals in the accompanying drawings include: 1. Insole; 2. Elastic diaphragm; 3. Base layer; 4. Flexible pressure sensor array; 5. Air chamber; 6. Elastic support sheet; 7. Airbag; 8. Channel; 9. Ball bearing; 10. Pin; 11. Through groove; 12. Pressure-sensitive resistor; 13. Air duct; 14. Auxiliary air duct; 15. First solenoid valve; 16. Second solenoid valve; 17. Air pump; 18. Shock-absorbing foam; 19. Partition. Detailed Implementation

[0040] The technical solution of the present invention will now be clearly and completely described with reference to the accompanying drawings. Obviously, the described embodiments are only some, not all, of the embodiments of the present invention. Based on the embodiments of the present invention, all other embodiments obtained by those skilled in the art without creative effort are within the scope of protection of the present invention.

[0041] In the description of this invention, it should be noted that the terms "center," "upper," "lower," "left," "right," "vertical," "horizontal," "inner," and "outer," etc., indicate the orientation or positional relationship based on the orientation or positional relationship shown in the accompanying drawings. They are used only for the convenience of describing the invention 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 the invention. Furthermore, the terms "first," "second," and "third" are used for descriptive purposes only and should not be construed as indicating or implying relative importance.

[0042] In the description of this invention, it should be noted that, unless otherwise explicitly specified and limited, the terms "installation," "connection," and "linking" 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 of two components. Those skilled in the art can understand the specific meaning of the above terms in this invention based on the specific circumstances.

[0043] The following detailed description illustrates the specific implementation method:

[0044] Example 1:

[0045] As attached Figure 1 , Figure 2 and Figure 7 The image shows a wearable assistive device for exercise rehabilitation in patients with diabetes and obesity, comprising a microcontroller and a plantar pressure adjustment component. The plantar pressure adjustment component includes an insole 1 with several openings located at the forefoot, arch, and heel. Specifically, the openings at the forefoot correspond to the big toe, the second and third toe balls, and the fourth and fifth toe balls; the openings at the arch correspond to the medial and lateral arches; and the openings at the heel correspond to the medial and lateral sides of the heel. The openings are independently configured according to the anatomical regions of the forefoot, arch, and heel to adapt to the physiological structure and stress characteristics of different areas of the foot, enabling subsequent zoned pressure adjustment.

[0046] The insole 1 has several elastic diaphragms 2 integrally formed on the top for closing the opening; the insole 1 is provided with a sensing component for monitoring foot pressure, the sensing component is located below the elastic diaphragms 2 and the sensing component is connected to the microcontroller signal.

[0047] like Figure 3 As shown, the sensing component includes several sets of flexible pressure sensor arrays 4. The flexible pressure sensor arrays 4 are used to monitor the pressure on the sole of the foot and transmit the pressure signal to the microcontroller. Each set of flexible pressure sensor arrays 4 is arranged in an equilateral triangle along the circumference of the opening. The flexible pressure sensor arrays 4 are all located below the elastic diaphragm 2 and are all fixedly connected to the insole 1.

[0048] Specifically, when walking, the sole of the foot applies pressure to the insole 1, and the elastic diaphragm 2 undergoes elastic deformation under the pressure of the sole of the foot, and then adheres downward to the flexible pressure sensor array 4 below it; since each set of flexible pressure sensor arrays 4 is arranged in an equilateral triangle along the circumference of the opening, it can collect pressure data after the elastic diaphragm 2 is deformed in all directions, and then transmit the pressure data to the microcontroller.

[0049] like Figure 3 and Figure 4 As shown, a base layer 3 is glued and fixed to the bottom of the insole 1. Several air cavities 5 are opened in the base layer 3, and each air cavity 5 is connected to its adjacent opening. Each air cavity 5 is provided with a folding component to enhance the support stiffness of the elastic diaphragm 2.

[0050] like Figure 6 As shown, a mounting groove is formed at the heel of the base layer 3, and a pump assembly is installed in the mounting groove. The pump assembly is electrically connected to the microcontroller, and the output end of the pump assembly is connected to an air guide pipe 13; Figure 4 and Figure 5As shown, the other end of the air duct 13 is connected to the air chamber 5. The air duct 13 is used to deliver gas into the air chamber 5 to deform the elastic diaphragm 2 and adjust the support stiffness of the insole 1. A first solenoid valve 15 is connected to the connection between the air chamber 5 and the air duct 13. The first solenoid valve 15 is electrically connected to the microcontroller. In this embodiment, the pump assembly is an air pump 17, and the input end of the air pump 17 is connected to an external air source.

[0051] Specifically, the microcontroller analyzes the pressure distribution of the sole of the foot based on the pressure data transmitted by the flexible pressure sensor array 4. If it detects that the pressure in a certain area exceeds a preset threshold (such as excessive pressure on the outer side of the heel) or that the pressure distribution is uneven (such as insufficient pressure on the arch of the foot), it immediately sends a control command to the pump assembly and the first solenoid valve 15 of the corresponding air chamber 5. After the pump assembly starts, it generates compressed gas, which is delivered to the target air chamber 5 through the air guide tube 13 and the first solenoid valve 15. This pushes the elastic diaphragm 2 to bulge upward, increasing the support stiffness of the corresponding area and dispersing the local pressure. When the pressure returns to a safe range, the microcontroller controls the pump assembly to stop working and the first solenoid valve 15 to close. The air chamber 5 maintains a stable pressure, ensuring that the sole of the foot is subjected to balanced force during walking.

[0052] like Figure 5 As shown, the folding assembly includes an airbag 7, which is fixedly connected to the side wall of the air chamber 5. An "N"-shaped elastic support piece 6 is fixedly connected inside the airbag 7, folding the airbag 7 into an "N" shape in the initial state. Several auxiliary air pipes 14 are connected to the air guide tube 13, with the other end of each auxiliary air pipe 14 connected to its adjacent airbag 7. A second solenoid valve 16 is connected at the connection point between the auxiliary air pipe 14 and the air guide tube 13, and each second solenoid valve 16 is electrically connected to a single-chip microcomputer. Figure 8 As shown, the gaps between the two sides of the airbag 7 and the sidewalls of the air chamber 5 form the channel 8.

[0053] Specifically, in the initial state, the airbag 7 is folded under the support of the elastic support plate 6. At this time, the airflow inside the air cavity 5 is kept unobstructed through the channels 8 on both sides of the airbag 7. In this embodiment, the installation position of the first solenoid valve 15 is offset from the installation position of the airbag 7 and is not on the same vertical plane. Therefore, when the gas enters the air cavity 5 through the first solenoid valve 15, it will not directly act on the area directly below the airbag 7.

[0054] When the microcontroller determines that a certain area needs to be reinforced with increased support rigidity, it controls the second solenoid valve 16 of the corresponding air chamber 5 to open. Gas is filled into the airbag 7 through the auxiliary air pipe 14. After the airbag 7 is inflated, it gradually expands, pushing the elastic support plate 6 to unfold and causing the airbag 7 to change from a folded state to an arc-shaped support state, providing additional rigid support for the elastic diaphragm 2.

[0055] During walking, the pressure on the sole of the foot first acts on the elastic diaphragm 2 and is transmitted to the air chamber 5. If the pressure is low, the unfolded elastic diaphragm 2 deforms slightly due to its own elasticity to achieve flexible support. If the pressure is high, the elastic support plate 6 and the inflated airbag 7 share the pressure with the gas in the elastic diaphragm 2 and the air chamber 5. When the pressure in this area returns to a safe range, the microcontroller controls the second solenoid valve 16 to open, and the gas will flow back into the air guide tube 13. In this embodiment, the air guide tube 13 is 30cm long and is fixed in a coiled shape in the base layer 3 to provide space for gas flow. Therefore, the air pressure in the inflated airbag 7 is greater than the air pressure in the air guide tube 13. Combined with the self-resetting elasticity of the elastic support plate 6, gas can flow from the high-pressure area to the low-pressure area. Under the action of its own elasticity, the elastic support plate 6 drives the airbag 7 to fold back, so that the support stiffness returns to the initial state and adapts to the force changes in different stages of the gait cycle.

[0056] like Figure 3 and Figure 5 As shown, the airbag 7 is equipped with a ball bearing 9, which is initially located at the lowest point of the fold of the "N"-shaped elastic support sheet 6; several ejector pins 10 are slidably fitted on the inner sidewall of the base layer 3, one end of each ejector pin 10 extends into the adjacent airbag 7 and is located at the top of the elastic support sheet 6 together with the ball bearing 9; several through slots 11 are opened in the base layer 3, and a varistor 12 is fixedly connected in each through slot 11, and the varistor 12 is electrically connected to the single-chip microcomputer; the other end of each ejector pin 10 extends into the adjacent through slot 11 and contacts the varistor 12.

[0057] Specifically, after the airbag 7 inflates, it pushes the elastic support plate 6 to unfold, causing the airbag 7 to change from a folded state to an arc-shaped support state. The ball bearing 9 rolls along the inclined surface of the unfolded elastic support plate 6, pushing the ejector pin 10 to slide towards the through groove 11. The squeezing force of the ejector pin 10 on the pressure-sensitive resistor 12 increases accordingly. The pressure-sensitive resistor 12 converts the squeezing force applied by the ejector pin 10 into a real-time resistance signal. The greater the pressure, the more obvious the change in resistance value. After receiving this signal, the microcontroller judges the air pressure in the corresponding airbag 7, and then combines it with the pressure data of the flexible pressure sensor array 4 to judge the actual stress intensity of the corresponding area. If the pressure is still detected to exceed the preset threshold, the inflation volume of the airbag 7 is increased again, so that the elastic support plate 6 is further unfolded and the support stiffness is strengthened. At the same time, the ball bearing 9 continuously adjusts the force of pushing the ejector pin 10 as the airbag 7 inflates, and feeds back the resistance signal of the pressure-sensitive resistor 12 to the microcontroller until the pressure in that area of ​​the foot returns to a safe range, realizing real-time adjustment of the foot support stiffness and avoiding local overload.

[0058] This embodiment monitors plantar pressure, capturing pressure in different areas of the foot in real time. By inflating or deflating the airbag 7, combined with the elastic deformation of the elastic support plate 6, plantar pressure is specifically dispersed. Simultaneously, the displacement of the ball bearing 9 drives the pin 10 to compress the feedback signal of the pressure-sensitive resistor 12, optimizing the support force of the airbag 7. This achieves real-time balance of plantar force during the gait cycle, effectively relieving local pressure during walking in diabetic and obese patients, reducing the risk of plantar injury, and improving the comfort and safety of sports rehabilitation.

[0059] Example 2:

[0060] As attached Figure 6 As shown, the difference from Embodiment 1 is that a partition 19 is fixedly connected in the mounting groove, the partition 19 divides the mounting groove into a control chamber and an adjustment chamber, the pump assembly is located in the adjustment chamber and shock-absorbing foam 18 is fixedly connected in the adjustment chamber.

[0061] Specifically, the shock-absorbing foam 18 can absorb the vibration and noise generated when the pump assembly is working, reducing the possibility of vibration being transmitted to the surface of the insole 1 through the base layer 3; when walking, the heel repeatedly applies pressure to the corresponding area of ​​the base layer 3, and the shock-absorbing foam 18 can also buffer the impact of the heel pressure on the pump assembly, ensuring that the pump assembly can still stably deliver gas under continuous pressure.

[0062] The control cavity houses a posture sensing component, which includes a MEMS integrated chip. The axis of the MEMS integrated chip is coaxially mounted with the foot's movement trajectory. The MEMS integrated chip incorporates a three-axis accelerometer and a three-axis gyroscope. The three-axis accelerometer is used to collect the acceleration changes of the foot in three-dimensional space and convert them into motion intensity, cadence, and stride length data. The three-axis gyroscope is used to collect the angular velocity changes of the foot around three-dimensional axes. The MEMS integrated chip transmits the motion intensity, cadence, stride length data, and angular velocity change data to the microcontroller.

[0063] Specifically, during walking, the three-axis accelerometer captures the acceleration changes of the foot in three-dimensional space (forward / backward, left / right, and up / down) in real time and converts them into motion intensity, cadence, and stride length data. Simultaneously, the three-axis gyroscope collects the angular velocity changes of the foot around the three-dimensional axes of roll, pitch, and yaw, recording the posture deflection of the foot during heel strike, arch support, and forefoot push-off in the gait cycle. The MEMS integrated chip transmits the collected and preprocessed motion intensity, cadence, stride length, and angular velocity change data to the microcontroller in real time. The microcontroller performs multi-source fusion analysis on these motion posture data, along with the plantar pressure data from the flexible pressure sensor array 4 and the feedback data from the pressure-sensitive resistor 12, to determine the force phase in the normal gait cycle and identify abnormal postures such as heel deviation and arch collapse. This provides a decision-making basis for the dynamic adjustment of the support stiffness of the air chamber 5, improving the accuracy and adaptability of the plantar support adjustment.

[0064] Example 3:

[0065] The difference from Embodiment 2 is that it also includes a physiological signal acquisition component and a blood glucose intelligent regulation system. The physiological signal acquisition component is used to collect heart rate variability data, skin conductance response data, and CGM blood glucose change data, and transmits the heart rate variability data, skin conductance response data, and CGM blood glucose change data to the blood glucose intelligent regulation system. In this embodiment, the physiological signal acquisition component can be a smart wristband or a continuous glucose monitor from the prior art, and is connected to a microcontroller. The blood glucose intelligent regulation system is connected to the microcontroller and includes a multi-signal preprocessing module and a blood glucose trend prediction model.

[0066] The multi-signal preprocessing module is used to denoise and standardize heart rate variability data, skin conductance response data, CGM blood glucose change data, exercise intensity, cadence, stride length data, and angular velocity change data, and extract feature parameters. The blood glucose trend prediction model is used to train an LSTM neural network model based on massive amounts of heart rate variability data, skin conductance response data, and CGM blood glucose change data in patient exercise scenarios, and learn the leading correlation between heart rate variability data, skin conductance response data, exercise intensity, and blood glucose changes 5-15 minutes later.

[0067] Specifically, when users exercise while wearing a smart wristband and a continuous glucose monitor, real-time data on heart rate variability, skin conductance response, and CGM blood glucose changes are collected. At the same time, the microcontroller transmits the exercise intensity, cadence, stride length, and angular velocity change data output by the MEMS integrated chip to the intelligent blood glucose control system. The multi-signal preprocessing module performs noise reduction processing on various types of data, filters out signal fluctuations caused by exercise interference, and extracts characteristic parameters such as heart rate variability time-domain indicators, skin conductance response peak, blood glucose change rate, and exercise intensity coefficient.

[0068] The blood glucose trend prediction model uses a large amount of physiological and exercise data from diabetic patients in exercise scenarios. The data is input into an LSTM neural network model, which learns the leading correlation between heart rate variability, skin conductance response, exercise intensity and blood glucose changes 5-15 minutes later. It obtains the relationship between changes in autonomic nervous activity, energy consumption and blood glucose fluctuations, and outputs the predicted blood glucose value and trend for the next 5-15 minutes, which is then synchronously fed back to the microcontroller.

[0069] Example 4:

[0070] The difference from Example 3 is that the intelligent blood glucose control system also includes a multivariate intervention module. This module integrates CGM blood glucose change data, in vivo insulin dosage, carbohydrate intake, and exercise intensity data. It simulates intervention measures using a multivariate linear regression model and outputs suggestions to the smart wristband to stabilize blood glucose within a safe range. In vivo active insulin dosage and recent carbohydrate intake are obtained through a user input system.

[0071] Specifically, the multivariate linear regression model was trained based on massive amounts of exercise intervention data from diabetic patients, and the formula is as follows:

[0072] △BG = (K1×I) - (K2×C) - (K3×S) + (K4×BG);

[0073] △BG represents the change in blood glucose after intervention; I represents the dose of active insulin in the body; K1 represents the insulin's glucose-lowering efficiency; C represents the planned amount of carbohydrates to be supplemented; K2 represents the carbohydrate's glucose-raising efficiency; S represents the exercise intensity coefficient; K3 is positively correlated with body weight; BG represents the current rate of change in blood glucose; and K4 is used to correct for trend inertia.

[0074] For the predicted glycemic risk, the multivariate intervention module automatically generates three types of intervention plans and calculates the final glycemic value under each plan using formulas: Carbohydrate supplementation plan: Three pre-set supplementation dose gradients (e.g., 10g, 15g, 20g) are calculated to determine the extent of glycemic rebound after supplementation and whether hypoglycemia can be avoided. Insulin adjustment plan: Two pre-set adjustment gradients (e.g., adding 0.5U, 1U, or pausing the next injection) are calculated to determine the extent of glycemic reduction and whether hyperglycemia can be suppressed. Exercise intensity adjustment plan: Two pre-set intensity gradients (e.g., decreasing cadence by 20 steps / minute, increasing cadence by 20 steps / minute) are calculated to determine the change in glycemic consumption rate and whether stable fluctuations can be achieved.

[0075] The optimal plan is selected based on the principles of safety and convenience: Priority 1: Plans that are easy to implement during exercise (prioritizing carbohydrate supplementation, then adjusting exercise intensity, and finally adjusting insulin to avoid the operational risks of insulin injection during exercise). Priority 2: Plans with precise effects (ensuring that blood glucose levels fall within a safe range after intervention, with an error ≤0.5mmol / L); Exclusion criteria: If a plan may cause blood glucose levels to exceed the safe range (e.g., supplementing with 20g of carbohydrates will cause blood glucose to rise to 11.5mmol / L), it will be directly eliminated.

[0076] Obviously, the above embodiments are merely illustrative examples for clear explanation and are not intended to limit the implementation. Those skilled in the art will recognize that other variations or modifications can be made based on the above description. It is neither necessary nor possible to exhaustively list all possible implementations here. However, obvious variations or modifications derived therefrom are still within the scope of protection of this invention.

Claims

1. A wearable assistive device for sports rehabilitation suitable for patients with diabetes and obesity, characterized in that, It includes a microcontroller and a foot pressure adjustment component; the foot pressure adjustment component includes an insole (1), which has several openings, and several elastic diaphragms (2) for closing the openings are fixedly connected to the top of the insole (1); the insole (1) is provided with a sensing component for monitoring foot pressure, the sensing component is located below the elastic diaphragms (2) and the sensing component is connected to the microcontroller signal. The bottom of the insole (1) is fixedly connected to a base layer (3), and the base layer (3) has several air cavities (5) inside, and each air cavity (5) is connected to its adjacent opening; each air cavity (5) is provided with a folding component to enhance the support stiffness of the elastic diaphragm (2); The base layer (3) has an installation groove at the heel, and a pump assembly is installed in the installation groove. The pump assembly is electrically connected to a single-chip microcomputer. The output end of the pump assembly is connected to an air guide pipe (13). The other end of the air guide pipe (13) is connected to the air chamber (5). The air guide pipe (13) is used to deliver gas into the air chamber (5) to deform the elastic diaphragm (2) and adjust the support stiffness of the insole (1). The air chamber (5) and the air guide pipe (13) are connected to a first solenoid valve (15). The first solenoid valve (15) is electrically connected to a single-chip microcomputer.

2. The wearable assistive device for sports rehabilitation of diabetic and obese patients according to claim 1, characterized in that, The openings are located at the forefoot, arch, and heel of the insole (1). The openings at the forefoot correspond to the big toe ball, the second-third toe ball, and the fourth-fifth toe ball, respectively. The openings at the arch correspond to the medial arch and the lateral arch, respectively. The openings at the heel correspond to the medial and lateral sides of the heel, respectively.

3. The wearable assistive device for sports rehabilitation of diabetic and obese patients according to claim 2, characterized in that, The sensing component includes several sets of flexible pressure sensor arrays (4). The flexible pressure sensor arrays (4) are used to monitor the pressure on the sole of the foot and transmit the pressure signal to the microcontroller. Each set of flexible pressure sensor arrays (4) is arranged in an equilateral triangle along the circumference of the opening. The flexible pressure sensor arrays (4) are all located below the elastic diaphragm (2) and are all fixedly connected to the insole (1).

4. The wearable assistive device for sports rehabilitation of diabetic and obese patients according to claim 3, characterized in that, The folding assembly includes an airbag (7), which is fixedly connected to the side wall of the air chamber (5). An "N"-shaped elastic support piece (6) is fixedly connected inside the airbag (7). The elastic support piece (6) folds the airbag (7) into an N-shape in the initial state. Several auxiliary air tubes (14) are connected to the air guide tube (13). The other end of each auxiliary air tube (14) is connected to the adjacent airbag (7). A second solenoid valve (16) is connected at the connection between the auxiliary air tube (14) and the air guide tube (13). The second solenoid valve (16) is connected to the single-chip microcomputer. The gap between the two sides of the airbag (7) and the side wall of the air chamber (5) forms a channel (8).

5. The wearable assistive device for sports rehabilitation of diabetic and obese patients according to claim 4, characterized in that, The airbag (7) is equipped with a ball bearing (9), which is initially located at the lowest point of the folded "N"-shaped elastic support sheet (6); the inner wall of the base layer (3) is slidably fitted with several ejector pins (10), one end of each ejector pin (10) extends into the airbag (7) adjacent to it and is located at the top of the elastic support sheet (6) together with the ball bearing (9); several through slots (11) are opened in the base layer (3), and each through slot (11) is fixedly connected with a pressure-sensitive resistor (12), which is electrically connected to a single-chip microcomputer; the other end of each ejector pin (10) extends into the through slot (11) adjacent to it and contacts the pressure-sensitive resistor (12).

6. The wearable assistive device for sports rehabilitation of diabetic and obese patients according to claim 5, characterized in that, A partition (19) is fixedly connected inside the mounting slot. The partition (19) divides the mounting slot into a control chamber and an adjustment chamber. The pump assembly is located inside the adjustment chamber and shock-absorbing foam (18) is fixedly connected inside the adjustment chamber.

7. The wearable assistive device for sports rehabilitation of diabetic and obese patients according to claim 6, characterized in that, The control cavity houses a posture sensing component, which includes a MEMS integrated chip. The axis of the MEMS integrated chip is coaxially mounted with the foot's movement trajectory. The MEMS integrated chip incorporates a three-axis accelerometer and a three-axis gyroscope. The three-axis accelerometer is used to collect the acceleration changes of the foot in three-dimensional space and convert them into motion intensity, cadence, and stride length data. The three-axis gyroscope is used to collect the angular velocity changes of the foot around three-dimensional axes. The MEMS integrated chip transmits the motion intensity, cadence, stride length data, and angular velocity change data to the microcontroller.

8. The wearable assistive device for sports rehabilitation of diabetic and obese patients according to claim 7, characterized in that, It also includes a physiological signal acquisition component and a blood glucose intelligent regulation system; the physiological signal acquisition component is used to collect heart rate variability data, skin conductance response data and CGM blood glucose change data, and transmit the heart rate variability data, skin conductance response data and CGM blood glucose change data to the blood glucose intelligent regulation system.

9. The wearable assistive device for sports rehabilitation of diabetic and obese patients according to claim 8, characterized in that, The intelligent blood glucose control system is connected to a microcontroller; the intelligent blood glucose control system includes a multi-signal preprocessing module and a blood glucose trend prediction model. The multi-signal preprocessing module is used to perform noise reduction and standardization on heart rate variability data, skin conductance response data, CGM blood glucose change data, exercise intensity, cadence, stride length data and angular velocity change data, and extract feature parameters. The blood glucose trend prediction model is used to train an LSTM neural network model based on massive amounts of heart rate variability data, skin conductance data, and CGM blood glucose change data in patients' exercise scenarios. The model learns the leading correlation between heart rate variability data, skin conductance data, and exercise intensity and blood glucose changes 5-15 minutes later.

10. The wearable assistive device for sports rehabilitation of diabetic and obese patients according to claim 9, characterized in that, The intelligent blood glucose regulation system also includes a multivariate intervention module, which integrates CGM blood glucose change data, in vivo insulin dosage, carbohydrate intake and exercise intensity data, simulates intervention measures through a multivariate linear regression model, and outputs suggestions to stabilize blood glucose within a safe range.

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