Self-adaptive fluid insole and shoe comprising same

Abstract

The invention discloses a self-adaptive fluid insole and a shoe comprising the same. The self-adaptive fluid insole comprises an adjusting fluid pad, a flexible pressure sensor, an empty groove, a fixing bolt, a transmission line and a line groove. The fluid adjusting pad is located at the bottom end of the shoe pad and internally provided with fluid; the flexible pressure sensor comprises a sensing part located above the adjusting fluid pad and a driving circuit located behind the heel or on the sole, the sensing part is in attached contact with the foot sole of the patient, and compensation supporting force is further provided according to detected pressure distribution of the foot sole of the patient after reactive force supporting is provided through fluid. According to foot shapes and pressure characteristics of different patient groups, through self-adaptive adjustment of fluid and multi-section pressure detection of a flexible pressure sensor, the detection precision and information richness are improved, pressure dispersion and dynamic adjustment of supporting force are achieved, the plantar condition of a patient can be improved, even the arch is corrected to a certain degree, and the patient's health is improved. Arthropathy is prevented, and healthy walking time is prolonged.

Description

Technical Field

[0001] The present invention relates to the field of medical auxiliary devices, and particularly to an adaptive fluid insole and a shoe including the same. Background Art

[0002] In the fields of medical care and health care, diabetic foot and flat foot are relatively common foot diseases that seriously affect the quality of life of patients. Due to the long-term hyperglycemic state of diabetic patients, it will lead to neuropathy and angiopathy, resulting in reduced foot sensation, poor blood circulation, easy damage to foot skin and difficult wound healing. During daily walking or standing, even the normal plantar pressure distribution may cause excessive local pressure in diabetic foot patients, which may further lead to complications such as ulcers and infections, and even the risk of amputation in severe cases.

[0003] Flat foot patients have abnormal stress on the plantar fascia, muscles and other structures due to the collapse of the foot arch. When walking or exercising, the sole of the foot cannot get normal buffering and support, and it is easy to cause fatigue and pain. In the long run, it may also lead to lesions of joints such as knees and hips. In this case, the quality of life and daily activity ability of patients will be significantly affected.

[0004] At present, the traditional insoles on the market have many deficiencies. First of all, it is difficult for them to provide effective decompression protection and targeted support for diabetic foot patients. Due to the complex and changeable foot conditions of diabetic foot patients, traditional insoles cannot be dynamically adjusted according to the real-time plantar pressure distribution of patients, which is likely to cause problems such as excessive local pressure or insufficient support. Secondly, most of the existing ordinary insoles lack the adaptive design for the special structure of flat feet, and cannot be dynamically adjusted according to the deformation and pressure distribution characteristics of the soles of flat foot patients, and cannot meet their needs of relieving symptoms and improving foot function.

[0005] In addition, the existing insoles generally lack intelligent perception and adaptive adjustment functions. They cannot monitor the changes in the plantar pressure of patients in real time, nor can they automatically adjust the support strength and distribution according to these changes. This static and passive design is difficult to adapt to the foot needs of patients in different activity states and cannot provide continuous and effective protection and support.

[0006] With the progress of medical technology and the increasing attention of people to foot health, the market urgently needs an innovative insole solution. Such a solution should be able to specifically target the foot conditions of diabetic foot and flat foot patients, have the ability to intelligently perceive the changes in plantar pressure, and be able to adaptively adjust to provide precise support and buffering. Such a product can not only help patients relieve pain and reduce the incidence of complications, but also significantly improve their daily activity ability and quality of life.

[0007] In view of the above problems, the existing technology urgently needs to be improved. Summary of the Invention

[0008] To solve at least one problem existing in the prior art described above, the present application provides an adaptive fluid insole, which includes an adjustable fluid pad, a flexible pressure sensor, an empty groove, a fixing bolt, a transmission line, and a line groove;

[0009] Among them, the adjustable fluid pad is located at the bottom end of the insole, and there is fluid inside it, providing support for the sole of the foot by means of the reaction force generated by the fluid. The adjustable fluid pad is closely attached to the inner bottom surface of the shoe; the flexible pressure sensor includes a sensing part located above the adjustable fluid pad and a driving circuit located behind the heel or on the sole of the shoe. The sensing part is in contact with the sole of the patient's foot, and further provides a compensation support force according to the detected pressure distribution of the patient's foot after being supported by the reaction force provided by the fluid; the fixing bolt is fixed on the adjustable fluid pad; the empty groove is formed by the cooperation of the fixing bolt and the adjustable fluid pad; the transmission line is arranged in the line groove on the flexible pressure sensor, and the uppermost end of the transmission line is in the same plane as the uppermost end of the line groove.

[0010] In the adaptive fluid insole as described above, optionally, the thickness of the toe part of the insole is less than the thickness of the heel part.

[0011] In the adaptive fluid insole as described above, optionally, the thickness of the adjustable fluid pad is between 3 mm and 15 mm.

[0012] In the adaptive fluid insole as described above, optionally, the fixing bolts are arranged according to the layout of traditional Chinese medicine acupoints, and the fluid inside the adjustable fluid pad is gas or liquid.

[0013] In the adaptive fluid insole as described above, optionally, the sensing part of the flexible pressure sensor includes a substrate and a sealing material, positive and negative induction electrodes, and an internal resistance element; among them, the substrate and the sealing material are used to isolate the outside world and connect the pressure sensing area, and the inner side thereof needs to be kept highly flat and smooth; the positive and negative induction electrodes are composed of conductive materials and can adjust their flexibility, size, spacing, and shape according to application requirements; the internal resistance element is composed of a semiconductor material and is located between the positive and negative induction electrodes. The upper and lower electrodes are in contact through the semiconductor material to form a conduction path.

[0014] In the adaptive fluid insole as described above, optionally, the drive circuit of the flexible pressure sensor is sequentially connected to: an external power supply, an external resistor, an operational amplifier, an analog-to-digital converter, and a microcontroller unit; wherein, the external power supply is set according to the specific usage scenario, and the external resistor and the sensing part form a voltage division circuit; the operational amplifier is used to enhance the intensity of the original signal output by the sensing part; the analog-to-digital converter converts the amplified analog voltage signal into a digital voltage signal; the microcontroller unit receives the digital voltage signal from the analog-to-digital converter, calculates the total resistance value of the internal resistance element of the sensing part through the digital voltage signal, and calculates the pressure value and the change trend of the flexible pressure sensor according to the flexibility coefficients of the positive and negative induction electrodes; the output end of the microcontroller unit is communicatively connected to an external device.

[0015] In the adaptive fluid insole as described above, optionally, the microcontroller unit performs an equalizing adjustment on the pressure distribution of the patient's sole by adjusting the voltage, so as to adaptively adjust the thickness of the adjusting fluid pad.

[0016] In the adaptive fluid insole as described above, optionally, the internal resistance element includes a long contact resistor, a medium contact resistor, and a short contact resistor. A plurality of internal resistance elements are evenly distributed in the sensing part, and are sequentially connected to the circuit in order when the flexible pressure sensor is deformed by force, and are in a parallel state when a plurality of resistors are connected; the contact length of the long contact resistor is greater than that of the medium contact resistor, and the contact length of the medium contact resistor is greater than that of the short contact resistor.

[0017] In the adaptive fluid insole as described above, optionally, when the sensing part is under pressure, when the long contact resistor first accesses the circuit due to its long contact, the total voltage of the flexible pressure sensor at this time is:

[0018]

[0019] wherein, r1 is the total resistance of the long contact resistor in the sensing part, V cc is the voltage connected to the drive circuit, R is the external resistor, and V is the total voltage;

[0020] When the flexible pressure sensor is continuously under pressure and the medium contact resistor accesses the circuit, the total voltage of the flexible pressure sensor is:

[0021]

[0022] wherein, r2 is the total resistance of the medium contact resistor in the sensing part;

[0023] When the short contact resistor accesses the circuit, the total voltage of the flexible pressure sensor is:

[0024]

[0025] Among them, r3 is the total resistance of the short contact resistance in the sensing part.

[0026] To achieve the above object, a second aspect of the present invention further provides a shoe, which includes the adaptive fluid insole as described in any one of the foregoing first aspects.

[0027] Compared with the existing processing methods, the beneficial effects of the present application are as follows:

[0028] 1. For patients with diabetic foot, the adjustable fluid pad of the present adaptive fluid insole can adaptively adjust the internal fluid according to the plantar pressure distribution. By effectively dispersing the pressure and avoiding excessive local pressure, the risk of complications such as foot skin damage, ulcer formation, and infection caused by pressure concentration in diabetic foot patients is significantly reduced, providing a key protective barrier for the foot health of diabetic patients, helping to extend their healthy walking time, improve their self-care ability, and reduce the medical burden on families and society.

[0029] 2. For patients with flat feet, the design of the adjustable fluid pad combined with the fixed bolt can provide personalized arch support according to the special shape of flat feet and the characteristics of plantar pressure. During walking, as the plantar pressure changes, the internal fluid of the insole adjusts dynamically, assisting in maintaining the relative stability of the arch, relieving the excessive stretching of the plantar fascia and muscle fatigue caused by arch collapse, reducing pain symptoms. Long-term use helps to improve the condition of flat feet, and even plays a role in correcting the arch to a certain extent, preventing chain joint diseases such as knees and hips caused by flat feet, and improving the overall motor function and quality of life of patients.

[0030] 3. Further, by using a flexible pressure sensor to real-time monitor the plantar pressure distribution after the fluid is adaptively adjusted, and by setting a long contact resistance, a medium contact resistance, and a short contact resistance inside, and their contact lengths are different, they can be connected to the circuit in sequence according to the magnitude of the pressure received, and it is possible to achieve segmented detection of different pressure ranges. This multi-segment design can cover a wider pressure range, and provide richer information for different pressure stages, effectively improving the accuracy and resolution of pressure detection, so as to more accurately sense different degrees of pressure, and adjust the thickness of the fluid pad according to the detection results, thereby dynamically adjusting the support strength, having the advantages of real-time monitoring of plantar pressure distribution, dynamic adjustment of support strength, providing precise support and buffering.

[0031] In summary, the adaptive fluid insole provided by the present application and the shoes including the same can provide customized arch support according to the foot shapes and pressure characteristics of different patient groups. Through the adaptive adjustment of the fluid and the multi-segment pressure detection of the flexible pressure sensor, the detection accuracy and information richness are improved, and the dynamic adjustment of pressure dispersion and support strength is realized, thereby effectively dispersing the plantar pressure, reducing the risks of skin breakage, ulcer and infection caused by pressure concentration in diabetic foot patients, alleviating the plantar fascia stretching and muscle fatigue caused by arch collapse in flat-foot patients, and relieving pain. Long-term use of the adaptive fluid insole provided by the present application and the shoes including the same helps to improve the flat-foot condition, even correct the arch to a certain extent, prevent joint diseases, extend the healthy walking time of diabetic patients, improve the ability of self-care, reduce the medical burden on families and society, and enhance the overall motor function and quality of life of various patients.

[0032] The concept, specific structure and technical effects of the present application will be further described below in conjunction with the drawings to fully understand the purpose, features and effects of the present application. BRIEF DESCRIPTION OF THE DRAWINGS

[0033] To more clearly illustrate the technical solutions of the embodiments of the present invention, the drawings required for use in the embodiments or the description of the prior art will be briefly introduced below. Obviously, the drawings in the following description are only some embodiments of the present invention, and those of ordinary skill in the art can also obtain other drawings based on these drawings without creative efforts.

[0034] Figure 1 is an isometric view of the structure of an embodiment of an adaptive fluid insole of the present application;

[0035] Figure 2 is Figure 1 the bottom view of the structure of the adaptive fluid insole in ;

[0036] Figure 3 is Figure 1 the front view of the structure of the adaptive fluid insole in ;

[0037] Figure 4 is Figure 1 the top view of the structure of the adaptive fluid insole in ;

[0038] Figure 5 is Figure 1 the cross-sectional view of the structure of the front sole end of the adaptive fluid insole in ;

[0039] Figure 6 is Figure 1 the cross-sectional view of the structure of the rear heel end of the adaptive fluid insole in ;

[0040] Figure 7It is a schematic diagram of the circuit structure of an embodiment of the flexible pressure sensor in the adaptive fluid insole of the present application;

[0041] Figure 8 is Figure 7 a schematic diagram of the structure of an embodiment of the sensing part of the flexible pressure sensor in;

[0042] Figure 9 is Figure 7 a sample diagram of the measured points of the resistance value and pressure of the test data of the flexible pressure sensor in.

[0043] Explanation of reference numerals:

[0044] 1 - Adjusting fluid pad;

[0045] 2 - Flexible pressure sensor; 210 - Sensing part, 211 - Long contact resistance, 212 - Medium contact resistance, 213 - Short contact resistance; 220 - External resistance; 230 - Operational amplifier; 240 - Analog - digital converter; 250 - Micro - control unit;

[0046] 3 - Empty groove;

[0047] 4 - Fixing bolt;

[0048] 5 - Transmission line;

[0049] 6 - Line groove. Detailed implementation manners

[0050] To make the objectives, technical solutions, and advantages of the embodiments of the present application clearer, the technical solutions in the embodiments of the present application will be clearly and completely described below with reference to the accompanying drawings in the embodiments of the present application. Obviously, the described embodiments are some, but not all, of the embodiments of the present application. All other embodiments obtained by those of ordinary skill in the art based on the embodiments in the present application without creative efforts shall fall within the protection scope of the present application.

[0051] In the description of the present application, if the term "a plurality" appears, the meaning of "a plurality" is at least two, such as two, three, etc., unless otherwise specifically defined.

[0052] As Figures 1 to 6 shown, an adaptive fluid insole of the present application may include an adjusting fluid pad 1, a flexible pressure sensor 2, an empty groove 3, a fixing bolt 4, a transmission line 5, and a line groove 6.

[0053] In this embodiment, the adjusting fluid pad 1 is located at the bottom end of the insole. It is internally provided with fluid, and provides support for the sole of the foot by the reaction force generated by the fluid. Moreover, the adjusting fluid pad 1 is closely attached to the inner bottom surface of the shoe.

[0054] The flexible pressure sensor 2 may include a sensing part 210 located above the adjustable fluid pad 1 and a driving circuit located behind the heel or on the sole of the shoe. The sensing part 210 is in close contact with the patient's plantar surface and further provides a compensatory support force according to the detected plantar pressure distribution of the patient after the reaction force provided by the fluid.

[0055] The fixing bolts 4 are fixed on the adjustable fluid pad 1, and the empty grooves 3 are formed by the cooperation of the fixing bolts 4 and the adjustable fluid pad 1 to enhance the stability of the adjustable fluid pad 1. The transmission line 5 is arranged in the line groove 6 on the flexible pressure sensor 2, and the transmission line 5 is embedded therein, which not only protects the line but also ensures the flatness of the insole surface. The uppermost end of the transmission line 5 is in the same plane as the uppermost end of the line groove 6.

[0056] In the embodiment as Figure 1 and Figure 2 shown, the adjustable fluid pad 1 has 13 fixing bolts 4, which perform point fixing on the bottom end and the top end of the adjustable fluid pad 1, preventing large misalignments between the bottom end and the top end of the adjustable fluid pad 1 and providing plantar support to prevent collapse. The slope formed by the fixing bolts 4 and the adjustable fluid pad 1 can provide support and cushioning for the patient's plantar surface, preventing the patient's plantar surface from directly contacting the bottom end after the fluid in one part of the adjustable fluid pad 1 flows away. The empty groove 3 is conical. After the patient steps on the adjustable fluid pad 1, the empty groove 3 spreads around, enabling the fluid in the adjustable fluid pad 1 to spread evenly, improving the comfort of the patient's use. In this embodiment, the fixing bolts can also be arranged according to the layout of traditional Chinese medicine acupoints, and automatic massage can be provided when the user steps on it (such as walking).

[0057] Optionally, the thickness of the adjustable fluid pad 1 is between 3 mm and 15 mm. Within this thickness range, the insole can still maintain a certain flexibility and will not be too rigid, which is beneficial to the natural movement of the foot. This thickness range enables the fluid pad to dynamically adjust according to the changes in the plantar pressure of the user, providing personalized support for patients with diabetic feet and flat feet. Thus, the thickness range of 3 mm - 15 mm is technically easy to achieve, which can not only ensure the product performance but also not increase too much production difficulty and cost.

[0058] Specifically, the thickness of the adjustable fluid pad 1 can be precisely adjusted according to the needs of different users. For example, for users with a lighter weight or a more evenly distributed foot pressure, the thickness can be adjusted to within the range of 3 mm to 8 mm to provide moderate support and cushioning. For users with a heavier weight or uneven foot pressure distribution, the thickness can be adjusted to within the range of 8 mm to 15 mm to provide stronger support and pressure dispersion effect. Specifically, the thickness of the adjustable fluid pad 1 can be automatically adjusted by the micro control unit 250 according to the plantar pressure distribution detected by the flexible pressure sensor 2. When it is detected that the pressure in certain areas is too high, the micro control unit 250 can increase the thickness of the fluid pad in that area, and vice versa, thereby achieving dynamic pressure balance.

[0059] In another alternative embodiment, the thickness of the toe part of the insole is less than that of the heel part. This design conforms to the natural structure of the human foot because the heel part usually bears more pressure than the toe part and requires a thicker cushioning layer. At the same time, the thinner thickness of the toe part can provide better flexibility, which is beneficial for the pushing-off action during walking.

[0060] Specifically, this thickness difference design can be achieved in various ways. For example, additional cushioning materials can be added to the heel part of the adjustable fluid pad 1, or the heel part can be directly designed to be thicker when manufacturing the adjustable fluid pad 1. Another method is to add an additional sensing layer to the heel part of the flexible pressure sensor 2, thereby increasing the overall thickness. As a preferred implementation method, the thickness of the heel part can be set to 10 - 15 mm, while the thickness of the toe part can be set to 5 - 8 mm. This thickness difference can ensure sufficient support while maintaining the overall thinness and lightness of the insole.

[0061] In actual use, when the user puts on the shoes equipped with this insole, the heel first contacts the thicker part and obtains a good cushioning effect. As the center of gravity moves forward, the thin design of the toe part allows for a more natural foot bend, which helps to maintain a normal gait. At the same time, the flexible pressure sensor 2 continuously monitors the plantar pressure distribution and makes real-time adjustments by adjusting the fluid pad 1 to ensure the best support state during walking or standing. This design is particularly suitable for patients with diabetic feet and flat feet. For patients with diabetic feet, the additional thickness of the heel part can better disperse the pressure and reduce the risk of excessive local pressure. For patients with flat feet, the thickness difference design helps to simulate the support effect of a normal foot arch and improve the foot force condition.

[0062] Adjust the fluid inside the fluid pad 1 to be gas or liquid. There are differences in compressibility between gas and liquid, providing more functional options for the insole. Gas has higher compressibility and can provide a softer buffering effect, which is suitable for patients who need to reduce the impact on the sole of the foot. Liquid has lower compressibility and can provide more stable support, which is suitable for flat-foot patients who need to strengthen the arch support. This differential characteristic enables the insole to be adjusted according to the specific needs of different patients, enhancing the applicability of the product.

[0063] By selecting liquids with different viscosities or gases with different pressures, the personalized needs of different patients can be further met. For example, for patients with a lighter weight, low-viscosity liquid or low-pressure gas can be selected; for patients with a heavier weight, high-viscosity liquid or high-pressure gas can be selected. This flexibility enables the insole to provide appropriate support and buffering for a wide range of patient groups. In addition, compared with solid materials, gases and liquids have lower densities, which helps to reduce the overall weight of the insole. This characteristic has a positive effect on improving the comfort of patients and reducing the energy consumption during walking, which is particularly important for diabetic foot patients with limited mobility.

[0064] In specific implementation, appropriate fluid types and parameters can be selected according to the specific situation of the patient. For example, for flat-foot patients who need stronger support, silicone oil with a higher viscosity can be selected as the liquid filler, and its viscosity can be in the range of 500 - 1000 cSt (centistokes). This high-viscosity liquid can provide stable support while still maintaining a certain degree of fluidity to adapt to the shape change of the foot. For diabetic foot patients who need more buffering effect, inert gases such as nitrogen or helium can be selected as the filler, and the air pressure can be adjusted in the range of 0.5 - 2 bar. This gas filling can provide a soft buffering effect and reduce the risk of excessive local pressure on the sole of the foot.

[0065] For example, for patients with mild flat feet, a fluid pad 1 with a thickness of 8 - 10 mm can be selected and filled with silicone oil of medium viscosity (about 700 cSt). For severe diabetic foot patients, a fluid pad 1 with a thickness of 12 - 15 mm can be selected and filled with nitrogen at a pressure of 1.5 bar. This combination of thickness and fluid can provide sufficient support and buffering while maintaining the lightness of the insole.

[0066] As Figure 7 and Figure 8 shown, the sensing part 210 of the flexible pressure sensor 2 can include a substrate, a sealing material, positive and negative sensing electrodes, and an internal resistance element.

[0067] Specifically, the base material and the sealing material are used to isolate the outside world and connect the pressure sensing area (i.e., the sensing part 210), and their inner sides need to be kept highly flat and smooth. The positive and negative sensing electrodes, made of conductive materials, can adjust their flexibility, size, spacing, and shape according to application requirements. The internal resistance element, made of a semiconductive material, is located between the positive and negative sensing electrodes, has a definite and stable conductivity, and the upper and lower electrodes are in contact through the semiconductive material to form a conduction path.

[0068] In this embodiment, as Figure 8 shown, the internal resistance element may specifically include: a long contact resistance 211, a medium contact resistance 212, and a short contact resistance 213, and the contact lengths of the long contact resistance 211, the medium contact resistance 212, and the short contact resistance 213 are different. Moreover, multiple internal resistance elements can conduct the circuit by the force deformation of the flexible pressure sensor 2: generate deformation according to the pressure received by the flexible pressure sensor 2 and connect to the circuit in sequence, and both ends of the sensing part 210 can be connected to the driving circuit through the sensor interface to provide a voltage source.

[0069] Furthermore, in an alternative embodiment, the long contact resistance 211 plays a key role in solving the problem of providing initial pressure information. When the flexible pressure sensor 2 is under pressure, due to its longer contact, the long contact resistance 211 is first connected to the circuit. At this time, through the change of the resistance of the long contact resistance 211 and the change of the voltage division relationship, the initial pressure information can be provided. This design enables the pressure sensor to immediately feedback the pressure information when initially under pressure, which helps to improve the response speed and initial accuracy of pressure detection. In this embodiment, the contact length of the long contact resistance 211 can be adjusted according to actual needs to optimize its response ability to the initial pressure.

[0070] The role of the medium contact resistance 212 is to be connected to the circuit when the pressure reaches a specific threshold, and this feature enables the sensor to provide more accurate detection in different pressure ranges. Similarly, the short contact resistance 213 is connected to the circuit when the pressure received exceeds the preset threshold, and together with the long contact resistance 211 and the medium contact resistance 212, they cover different pressure ranges to ensure the integrity and accuracy of pressure detection.

[0071] It can be seen from this that the collaborative work of the contact resistances with different lengths, through a multi-segment pressure detection method, can carefully distinguish and measure pressures of different magnitudes, thereby improving the accuracy and resolution of pressure detection, enabling the sensor to achieve higher-precision detection in different pressure ranges, cover a wider pressure range, and provide accurate measurement results in each pressure range.

[0072] The long contact resistance 211, the medium contact resistance 212, and the short contact resistance 213 can be evenly distributed within the sensing portion 210 and are in a parallel state when multiple resistors are connected. Specifically, the contact of the long contact resistance 211 is longer than that of the medium contact resistance 212, and the contact of the medium contact resistance 212 is longer than that of the short contact resistance 213. For example, the contact length of the long contact resistance 211 can be set to 5 - 10 mm, the contact length of the medium contact resistance 212 can be set to 3 - 7 mm, and the contact length of the short contact resistance 213 can be set to 1 - 5 mm. These contact lengths can be adjusted according to specific application scenarios to obtain the best pressure sensing effect.

[0073] When the sensing portion 210 is under pressure and the long contact resistance 211 is first connected to the circuit due to its longer contact, the total voltage of the flexible pressure sensor 2 at this time is:

[0074]

[0075] where r1 is the total resistance of the long contact resistance 211 in the sensing portion 210, V cc is the voltage connected to the driving circuit, R is the external resistance, and V is the total voltage.

[0076] When the flexible pressure sensor 2 is continuously stressed and the deformation of the sensing portion 210 reaches the contact of the medium contact resistance 212, the medium contact resistance 212 is connected to the circuit, and the total voltage of the flexible pressure sensor 2 at this time is:

[0077]

[0078] where r2 is the total resistance of the medium contact resistance 212 in the sensing portion 210.

[0079] When the force is further increased and the deformation of the sensing portion 210 reaches the contact of the short contact resistance 213, the short contact resistance 213 is connected to the circuit, and the total voltage of the flexible pressure sensor 2 at this time is:

[0080]

[0081] where r3 is the total resistance of the short contact resistance 213 in the sensing portion 210.

[0082] After the patient presses down the front end of the insole with the heel, the flexible pressure sensor 2 first starts to record the force application point and force application surface, and adjusts the fluid inside the fluid pad 1 to flow forward. The fluid inside the fluid pad 1 is adaptively adjusted as the sole of the foot applies force. When the sole of the foot applies full force, the fluid inside the fluid pad 1 reaches equilibrium, providing a reaction force relative to the sole of the foot, causing the upper end of the insole to closely adhere to the sole of the patient's foot and promoting force application on each part of the patient's sole. At this time, the long contact resistor 211 in the flexible pressure sensor 2 is first connected to the circuit. At this time, through the change in the resistance of the long contact resistor 211 and the change in the voltage division relationship, initial pressure information can be provided. When the pressure reaches a specific threshold, the middle contact resistor 212 is connected to the circuit. Similarly, the short contact resistor 213 is connected to the circuit when the applied pressure exceeds the preset threshold. When the patient takes the next step, the insole continues to adjust.

[0083] The drive circuit can be sequentially connected with an external power supply, an external resistor 220, an operational amplifier 230, an analog-to-digital converter 240, and a microcontrol unit 250.

[0084] Specifically, the external power supply can be set according to the specific usage scenario. The external resistor 220 and the sensing unit 210 together form a voltage division circuit. Since the original signal output by the sensing unit 210 may be relatively weak, the operational amplifier 230 can enhance the signal intensity, making it easier for subsequent processing and analysis, ensuring the stability and reliability of the signal during transmission, and reducing signal distortion and noise interference. The analog-to-digital converter 240 converts the amplified analog voltage signal into a digital voltage signal. The digital signal is convenient for the microcontrol unit 250 to process and analyze, realizing the connection between the analog signal and the digital system, making the output of the sensing unit 210 compatible with modern electronic control systems, and improving the accuracy and efficiency of data processing. The receiving end of the microcontrol unit 250 receives the digital voltage signal from the analog-to-digital converter 240, calculates the total resistance value of the internal resistance elements of the sensing unit 210 through the digital voltage signal, and calculates the pressure value and change trend received by the flexible pressure sensor 2 based on the flexible coefficients of the positive and negative induction electrodes. In this embodiment, the output end of the microcontrol unit 250 can be communicatively connected to an external device. Optionally, the external device can be a personal terminal, a server, or a network device, etc. For example, the microcontrol unit 250 can communicate with a smartphone application through a Bluetooth module, transmitting real-time pressure data and change trends to users or medical staff. The application can display a heat map of the plantar pressure distribution, and when an abnormal pressure distribution is detected, it can adaptively adjust the thickness of the fluid pad 1 by adjusting the voltage to balance the plantar pressure distribution of the patient.

[0085] The microcontroller unit 250 can adopt various algorithms to process the pressure information. For example, it can use the weighted average method, the least squares method, or machine learning algorithms to analyze the pressure distribution pattern. By changing the voltage, the microcontroller unit 250 can precisely control the distribution and pressure of the fluid inside the fluid pad 1. For example, the microcontroller unit 250 can finely adjust the voltage through PWM (Pulse Width Modulation) technology to achieve precise control of the fluid pressure. The voltage regulation range can be set between 0 - 5V and adjusted according to different pressure requirements.

[0086] The adjustable fluid pad 1 can adjust its own thickness by changing the distribution of the internal fluid according to the instructions of the microcontroller unit 250, so as to provide appropriate supporting force for different parts of the sole. As a preferred implementation manner, a plurality of pressure sensing regions can be arranged in the sensing part 210, and each region corresponds to a different part of the sole, such as the forefoot, the midfoot, and the heel. The shapes and densities of the positive and negative sensing electrodes can be independently designed for each region to adapt to the pressure characteristics of that region. For example, small-sized electrodes with a higher density can be arranged in the forefoot region to capture more subtle pressure changes; while larger-sized electrodes can be used in the heel region to withstand higher pressures.

[0087] For example, a 16×16 pressure sensing array can be arranged in the sensing part 210 to cover the entire sole area. The size of each sensing unit can be set to 1cm×1cm, and it includes a pair of positive and negative sensing electrodes and an internal resistance element. The positive and negative sensing electrodes are made of silver nanowire materials and fabricated by screen printing technology, and the electrode spacing is set to 200 microns. The internal resistance element is made of a carbon nanotube / PDMS composite material with a thickness of 50 microns. The substrate and the sealing material are made of medical-grade PDMS with a thickness of 1mm, and the flatness of the inner surface is controlled within the range of ±5 microns.

[0088] This design enables the sensor to accurately capture the pressure distribution of different regions of the sole. When the patient stands or walks, the plantar pressure will cause the internal resistance element in the corresponding region to deform, thereby changing its resistance value. By measuring the resistance change of each sensing unit, the pressure distribution map of the entire sole can be obtained. These data can be transmitted to the control system in real time for adjusting the supporting strength of the fluid insole, so as to provide personalized plantar pressure management for the patient.

[0089] Furthermore, the pressure sensing regions can also be partitioned according to the foot bone structure to maximize human comfort, relieve pressure, support the human body, and correct the sole.

[0090] In practical applications, the technical solution of this application can be implemented as follows: First, according to the patient's weight and foot condition, a suitable external power supply and external resistor 220 are selected. For example, for patients with a lighter weight, a 3.3V power supply and a 100Ω external resistor can be used; for patients with a heavier weight, a 5V power supply and a 220Ω external resistor can be used. The operational amplifier 230 can be set to a gain of 10 to ensure sufficient signal strength. The analog-to-digital converter 240 selects the ADS1115 with a 16-bit resolution, which can provide 65,536 digital quantization levels to ensure accurate measurement of the pressure value. The microcontroller unit 250 uses Arduino Nano, whose processing speed and storage capacity are sufficient to meet the requirements of real-time data processing. The microcontroller unit 250 communicates with the analog-to-digital converter 240 through the I2C interface, sampling 100 times per second to capture the rapid changes in plantar pressure. The algorithm in the microcontroller unit 250 calculates the total resistance value of the internal resistance element based on the digital voltage signal, and combines the pre-calibrated positive and negative induction electrode flexibility coefficients to deduce the actual pressure value. For example, when the digital voltage signal is 32,768 (i.e., the midpoint value of the 16-bit ADC), it may correspond to a pressure value of 500 kPa. The microcontroller unit 250 can also store the pressure data of the past 10 seconds, calculate the pressure change trend, and thus predict the possible pressure concentration areas.

[0091] Specifically, when the patient wears the shoes equipped with the adaptive fluid insole of this application, the flexible pressure sensor 2 immediately starts to detect the pressure distribution in each area of the sole. These pressure information are sent to the microcontroller unit 250 through the transmission line 5. The microcontroller unit 250 calculates the ideal pressure distribution state according to the preset pressure balance algorithm. Subsequently, the microcontroller unit 250 controls the pressure and distribution of the fluid in these areas by adjusting the voltage sent to each area of the adjustable fluid pad 1.

[0092] For example, if it is detected that the pressure in the forefoot area is too high, the microcontroller unit 250 will reduce the voltage sent to this area, causing the fluid to flow to other areas, thereby reducing the thickness and pressure of the forefoot area. At the same time, the heel area may receive a higher voltage, causing the fluid to gather and increase in thickness to provide more support for the heel. This process is continuous and can be carried out in real time during the patient's walking or standing, ensuring that the plantar pressure always remains in the optimal distribution state.

[0093] As a preferred embodiment, the micro control unit 250 can set multiple pressure thresholds. For example, the plantar pressure can be divided into three levels: low, medium, and high. When the pressure in a certain area exceeds the high-pressure threshold, the system will immediately adjust the fluid distribution in that area to prevent discomfort or injury caused by excessive local pressure. At the same time, the system can also automatically switch different pressure adjustment modes according to the patient's activity state (such as stationary, walking, running) to adapt to the pressure distribution requirements under different activity intensities.

[0094] In this embodiment, when different contact resistances in the sensing part 210 are connected, they jointly determine the voltage distribution in the circuit with the external resistor 220, thereby affecting the magnitude of the output voltage. This design is also an important part of calculating the voltage value corresponding to the pressure received by the sensor.

[0095] For example, a 20mm rubber test head is selected to test the flexible pressure sensor 2, and the experimental test data is shown in Table 1 below:

[0096] Pressure / kg 2 4 6 8 10 12 14 16 18 20 Resistance value / kΩ 20.55 13.55 11.38 10.38 9.81 9.46 9.22 9.05 8.94 8.85

[0097] Table 1

[0098] Based on the above data, a measurement point example diagram of resistance value and pressure as shown in Figure 9 can be generated, and the curve relationship between pressure and resistance value can be seen.

[0099] Another example, when the sensing part 210 is subjected to a pressure F and generates a deformation ε, the deformation formula is: F = kε. Where k is the deformation coefficient of the base material of the sensing part 210. For example, when the deformation of the sensing part 210 causes eight long contact resistors 211, five medium contact resistors 212, and three short contact resistors 213 to contact, the total resistance r at this time is: By the different numbers and lengths of the contact resistors in contact, the magnitude and direction of the external force applied to the sensor can be inferred.

[0100] Therefore, the change in the total resistance can be converted into the magnitude of the external force. Forces in different directions will cause different combinations of contact resistors to contact. By analyzing the distribution of the contact resistors in contact, the direction of the force can be inferred. For example, if mainly the long contact resistors 211 are in contact, it may indicate that the direction of the force is in a certain specific direction; if the medium contact resistors 212 and the short contact resistors 213 are in contact at the same time, it may indicate that the direction of the force is in another direction.

[0101] Furthermore, in an alternative embodiment, for applications that require measuring the pressure on a curved surface, the sensing portion 210 can be spiral or wavy to enhance flexibility and conformability. By designing the sensing portion 210 to be spiral or wavy, the flexible pressure sensor 2 can better conform to the curved surface, improving its application effect on surfaces with complex shapes. This shape design enables the flexible pressure sensor 2 to better adapt to the bending and deformation of the surface when subjected to external pressure, thereby achieving more accurate pressure measurement. The sensing portion 210 can use medical-grade silicone as the base material. In actual use, those skilled in the art can adopt mold forming technology to make the medical-grade silicone into the desired flexible base shape to ensure its close fit with the sensing components. It is also possible to form a thin layer of medical-grade silicone coating on other flexible materials by coating or casting to enhance the flexibility and biocompatibility of the overall structure.

[0102] To achieve the above object, the present application further provides a shoe, including the adaptive fluid insole described in any of the above embodiments. By combining the adaptive fluid insole with the shoe structure, better overall performance is achieved. The shoe can be designed accordingly based on the thickness and shape of the adaptive fluid insole to ensure the best balance between comfort and functionality.

[0103] In summary, the adaptive fluid insole and the shoe incorporating it proposed in the present application by combining fluid mechanics and segmented flexible pressure sensing can automatically adjust the support force according to pressure changes. The fluid can evenly distribute the pressure and provide a better buffering effect; at the same time, the fluidity of the fluid enables the insole to quickly respond to pressure changes and achieve dynamic adjustment. The introduction of the flexible pressure sensor 2 solves the problem of real-time monitoring and provides a data basis for intelligent adjustment. By adjusting the fluid pad 1 to provide basic support, the flexible pressure sensor 2 monitors the pressure distribution in real time and adjusts the fluid distribution according to the monitoring results, thereby achieving intelligent and balanced adjustment of the plantar pressure.

[0104] The above has described in detail the preferred specific embodiments of the present application, which only represent several implementation manners of the present application, but should not be construed as a limitation on the scope of the patent. The technical features of the above embodiments can be combined arbitrarily. For the sake of brevity, not all possible combinations of the technical features in the above embodiments have been described. However, as long as there is no contradiction in the combination of these technical features, it should be considered as the scope described in this specification. It should be understood that those of ordinary skill in the art can make many modifications and variations based on the concept of the present application without creative labor. Therefore, without departing from the concept of the present application, all technical solutions that can be obtained by those skilled in the art in the technical field of the present application based on the concept of the present application through logical analysis, reasoning, or limited experiments on the basis of the prior art should be within the protection scope determined by the claims.

Claims

1. An adaptive fluid insole, characterized in that: It comprises a regulating fluid pad (1), a flexible pressure sensor (2), an empty slot (3), a fixing bolt (4), a transmission line (5) and a line groove (6); The regulating fluid pad (1) is located at the bottom of the insole, and is provided with fluid inside. The fluid provides support for the sole of the foot by means of the reaction force generated by the fluid. The regulating fluid pad (1) is tightly fitted with the inner bottom surface of the shoe. The flexible pressure sensor (2) comprises a sensing part (210) located above the regulating fluid pad (1) and a driving circuit located behind the heel or the sole. The sensing part (210) is in contact with the sole of the patient's foot and further provides a compensatory support force according to the pressure distribution of the sole of the patient after the reaction force provided by the fluid is detected. The fixing bolt (4) is fixed on the regulating fluid pad (1). The empty groove (3) is formed by the fixing bolt (4) and the regulating fluid pad (1). The transmission line (5) is arranged in a line groove (6) on the flexible pressure sensor (2). The uppermost end of the transmission line (5) and the uppermost end of the line groove (6) are in the same plane.

2. The adaptive fluid insole according to claim 1, characterized in that The thickness of the toe part of the insole is smaller than the thickness of the heel part.

3. The adaptive fluid insole according to claim 1, characterized in that The thickness of the regulating fluid pad (1) is between 3 mm and 15 mm.

4. The adaptive fluid insole according to claim 1, characterized in that: The fixing bolt (4) is arranged according to the acupuncture points of traditional Chinese medicine, and the fluid inside the regulating fluid pad (1) is gas or liquid.

5. The adaptive fluid insole according to claim 4, characterized in that: The sensing part (210) of the flexible pressure sensor (2) comprises a substrate and a sealing material, positive and negative sensing electrodes and an internal resistance element; wherein the substrate and the sealing material are used to isolate the outside world and connect the pressure sensing area, and the inner side thereof needs to be kept highly flat and smooth; the positive and negative sensing electrodes are made of conductive material, and their flexibility, size, spacing and shape can be adjusted according to application requirements; the internal resistance element is made of semi-conductive material, and is located between the positive and negative sensing electrodes, and the upper and lower electrodes are in contact through the semi-conductive material to form a conductive path.

6. The adaptive fluid insole according to claim 5, characterized in that: The driving circuit of the flexible pressure sensor (2) is connected in sequence to: an external power supply, an external resistor (220), an operational amplifier (230), an analog-to-digital converter (240), and a microcontroller unit (250); wherein the external power supply is set according to a specific usage scenario, and the external resistor (220) and the sensing part (210) form a voltage divider circuit; the operational amplifier (230) is used to enhance the original signal strength output by the sensing part (210); the analog-to-digital converter (240) converts the amplified analog voltage signal into a digital voltage signal; the microcontroller unit (250) receives the digital voltage signal from the analog-to-digital converter (240), calculates the total resistance value of the internal resistance element of the sensing part (210) through the digital voltage signal, and infers the pressure value and change trend of the flexible pressure sensor (2) according to the flexibility coefficient of the positive and negative sensing electrodes; and the output end of the microcontroller unit (250) is connected to an external device for communication.

7. The adaptive fluid insole according to claim 6, characterized in that: The micro control unit (250) evenly adjusts the pressure distribution on the sole of the patient's foot by adjusting the voltage, thereby adaptively adjusting the thickness of the regulating fluid pad (1).

8. The adaptive fluid insole according to claim 6, characterized in that: The internal resistance element comprises a long contact resistance (211), a middle contact resistance (212) and a short contact resistance (213); a plurality of internal resistance elements are evenly distributed in the sensing portion (210); when the flexible pressure sensor (2) is deformed by force, the internal resistance elements are sequentially connected to the circuit, and when the plurality of resistances are connected, they are in a parallel state; the contact length of the long contact resistance (211) is greater than that of the middle contact resistance (212); and the contact length of the middle contact resistance (212) is greater than that of the short contact resistance (213).

9. The adaptive fluid insole according to claim 8, characterized in that: When the sensing part (210) is subjected to pressure, the long contact resistor (211) is first connected to the circuit due to its longer contact. At this time, the total voltage of the flexible pressure sensor (2) is: Wherein, r1 is the total resistance of the long contact resistor (211) in the sensing part (210), V cc is the voltage connected to the driving circuit, R is the external resistor, and V is the total voltage; When the flexible pressure sensor (2) is continuously subjected to force and the middle contact resistor (212) is connected to the circuit, the total voltage of the flexible pressure sensor (2) is: wherein r2 is the total resistance of the middle contact resistor (212) in the sensing portion (210); When the short contact resistor (213) is connected to the circuit, the total voltage of the flexible pressure sensor (2) is: Wherein, r3 is the total resistance of the short contact resistor (213) in the sensing part (210).

10. A shoe, characterized in that: Comprising the adaptive fluid insole as claimed in any one of claims 1 to 9.

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