Flexible wearable garment for measuring pressurized garment wear data

Abstract

The application discloses a flexible wearing clothes for measuring pressurized clothes wearing data, which comprises a body, a flexible sensor and a control device, the body is used for wearing between a human body and the pressurized clothes, and the flexible sensor is arranged on the body. The flexible sensor comprises an electromyography sensor, a strain sensor, an IMU sensor and a pressure sensor, the electromyography sensor is used for adhering to the surface of the human body to obtain the activation timing and the strength of the human muscle, the strain sensor is used for detecting the bending and stretching angle of the human joint, the IMU sensor is used for detecting the joint posture angle and the angular velocity of the human joint, and the pressure sensor is used for detecting the pressure received by the surface of the human body. The control device determines the pressure generated by the pressurized clothes and the influence of the pressurized clothes on the muscle strength and the movement posture based on the detection data obtained by the flexible sensor when the human body is in a naked wearing state and a wearing pressurized clothes state respectively, and analyzes the influence of the pressurized clothes on the muscle strength characteristics and the limb movement posture of the human body.

Description

Technical Field

[0001] This application relates to the field of wearable clothing technology, and more particularly to a flexible wearable garment for measuring data from pressure garment wear. Background Technology

[0002] The pressure exerted on the human body by compression garments directly affects the body's athletic performance and physiological state. Therefore, how to monitor compression garments under natural movement conditions and reflect their mechanical effects on the human body is of great practical significance and has broad application prospects for the optimized design of compression garments and the prevention of activity injuries. Summary of the Invention

[0003] This application aims to address at least one of the technical problems existing in the prior art or related technologies.

[0004] This application proposes a flexible wearable garment for measuring compression suit wearing data. The flexible wearable garment includes a main body, flexible sensors, and a control device. The main body is worn between the human body and the compression suit, and the flexible sensors are located on the main body. The flexible sensors include an electromyography (EMG) sensor, a strain sensor, an IMU sensor, and a pressure sensor. The EMG sensor is used to conform to the human body surface to obtain the activation sequence and force intensity of human muscles. The strain sensor is used to detect the bending and extension angles of human joints. The IMU sensor is used to detect the joint posture angles and angular velocities of human joints. The pressure sensor is used to detect the pressure on the human body surface. Based on the detection data obtained by the flexible sensors in both a naked wearing state and a wearing compression suit state, the control device determines the pressure generated by the compression suit and the influence of the compression suit on muscle force and movement posture.

[0005] In some of the technical solutions provided in this application, the electromyography sensor includes: a conductive cloth and an elastic element, the elastic element being located between the conductive cloth and the body, and the elastic element being used to make the conductive cloth adhere to the human body surface.

[0006] In some of the technical solutions provided in this application, the strain sensor and pressure sensor are capacitive sensors. The capacitive sensor includes a conductive layer and a dielectric layer, with the dielectric layer located between the two conductive layers.

[0007] In some of the technical solutions provided in this application, the flexible wearable garment also includes: a grounding shielding strip, which is disposed between the IMU sensor and the strain sensor, and the power supply pin of the IMU sensor is configured with a π-type filter network to suppress power supply ripple.

[0008] In some of the technical solutions provided in this application, the control device is used to calculate the joint attitude angle from the IMU sensor's detection data using the quaternion method, construct a gravity component compensation model, and remove interference values ​​from the strain sensor's detection data. The control device is also used to apply an adaptive Kalman filter algorithm to reduce noise in the strain sensor's detection data and perform second-order Butterworth low-pass filtering.

[0009] In some of the technical solutions provided in this application, the control device includes: a data acquisition module, which is connected to a flexible sensor via a flexible wire. The elastic modulus of the flexible sensor is lower than that of the flexible wire, and the flexible sensor is connected to the flexible wire via a modulus transition piece with a gradually changing modulus gradient.

[0010] In some technical solutions provided in this application, the body includes: an outer fabric and an inner fabric, a strain sensor, an IMU sensor and a pressure sensor located between the outer fabric and the inner fabric, an electromyography sensor located on the inner side of the inner fabric, and a flexible wire located between the outer fabric and the inner fabric.

[0011] In some of the technical solutions provided in this application, the body also includes: a hot melt mesh film, hot melt mesh films are respectively provided on one side of the outer fabric and the inner fabric, and on the inner side of the inner fabric, and the flexible sensor is disposed on the body through a hot pressing composite process.

[0012] In some of the technical solutions provided in this application, flexible sensors located in the right upper limb region of the human body are densely deployed. The right upper limb region includes: the right upper arm, the right forearm, and the right palm.

[0013] In some of the technical solutions provided in this application, the IMU sensor is located in the motion area of ​​the human body, including: the front of the shoulder joint, the back of the shoulder joint, the elbow joint, the hip joint, the thigh, the calf, the ankle joint, the back, the wrist joint, and the hand. The strain sensor and pressure sensor are located in the joint areas of the human body, including: the shoulder, elbow, hip, knee, and ankle.

[0014] Compared with related technologies, the present invention has at least the following beneficial effects: This invention breaks through the limitations of traditional measuring equipment, enabling the simultaneous acquisition of motion data and electromyographic signals of the human body in natural activity states, comprehensively and accurately reflecting the dynamic mechanical characteristics of the human body. Furthermore, by collecting full-condition data before and after pressurization of the pressure suit, it analyzes the impact of the pressure suit on the muscle exertion characteristics and limb movement posture, establishing a correlation model between pressure distribution, joint torque, and muscle physiological activity in special pressure suits. This allows for monitoring of dynamic resistance changes during human movement, meeting the long-term dynamic monitoring needs of pressure suits in various scenarios such as research and development and training, and providing scientific data support for the optimized design of special pressure suits. Attached Figure Description

[0015] Various other advantages and benefits will become apparent to those skilled in the art upon reading the following detailed description of some embodiments. The accompanying drawings are for illustrative purposes only and are not intended to limit the scope of this application. Furthermore, the same reference numerals denote the same parts throughout the drawings. In the drawings: Figure 1 This is a schematic diagram of the structure of a flexible wearable garment according to an embodiment of this application.

[0016] in, Figure 1 The correspondence between the reference numerals and component names in the attached drawings is as follows: 10. Flexible wearable clothing; 100. Body; 210. Electromyography sensor; 220. Strain sensor; 230. IMU sensor; 240. Pressure sensor; 250. Temperature sensor. Detailed Implementation

[0017] To better understand the above technical solutions, the technical solutions of the embodiments of this application will be described in detail below with reference to the accompanying drawings and specific embodiments. It should be understood that the embodiments of this application and the specific features in the embodiments are detailed descriptions of the technical solutions of the embodiments of this application, rather than limitations on the technical solutions of this application. In the absence of conflict, the embodiments of this application and the technical features in the embodiments can be combined with each other.

[0018] Embodiments of this application provide a flexible wearable garment 10 for measuring compression garment wearing data, such as... Figure 1 As shown, the flexible wearable garment 10 includes a body 100, flexible sensors, and a control device. The body 100 is worn between the human body and the pressure garment, and the flexible sensors are disposed on the body 100. The flexible sensors include an electromyography (EMG) sensor 210, a strain sensor 220, an IMU sensor 230, and a pressure sensor 240. The EMG sensor 210 is used to conform to the human body surface to obtain the activation sequence and force intensity of human muscles. The strain sensor 220 is used to detect the bending and extension angles of human joints. The IMU sensor 230 is used to detect the joint posture angles and angular velocities of human joints. The pressure sensor 240 is used to detect the pressure on the human body surface. Based on the detection data obtained by the flexible sensors when the human body is in a naked wearing state and in a wearing pressure garment state, the control device determines the pressure generated by the pressure garment and the influence of the pressure garment on muscle force and movement posture.

[0019] In this embodiment, the body 100 of the flexible wearable garment 10 is made of a highly elastic, breathable, and soft fabric to ensure the comfort and flexibility of the garment and avoid affecting normal joint movement. The body 100 is worn outside the human body, located between the pressure garment and the human body; the pressure garment can be a special type of pressure garment. When the human body wears only the flexible wearable garment 10, it is in a naked wearing state; when the human body wears both the flexible wearable garment 10 and the pressure garment, it is in a pressure garment wearing state. Flexible sensors are integrated inside the body 100 at key stress points corresponding to the joints. The flexible sensors are sweat-resistant and made of flexible materials, capable of adapting to complex joint movements, improving wearing comfort and human conformity. The flexible sensors are thin, soft, and do not interfere with or affect joint movement. The flexible sensors integrate multiple sensors such as electromyography, strain, inertia, and pressure, and can simultaneously collect information on muscle exertion, joint flexion and extension angles, angular velocity, and surface pressure.

[0020] Specifically, strain sensor 220 detects the bending and extension angles of the joint by collecting strain at the joint position and converting strain into angle. The detection range for bending and extension angles is 0° to 150°. IMU (Inertial Measurement Unit) sensors, through readings from a built-in three-axis accelerometer and three-axis gyroscope, can acquire joint attitude angles and angular velocity readings. Joint attitude angles include bending and extension angles, torsional angles, and other omnidirectional spatial deflection angles. The detection range for joint attitude angles is 0° to 360°. Pressure sensor 240 collects the pressure values ​​on the human body surface, capturing the pressure applied to the body by the pressure garment. The electromyography (EMG) sensor 210 acquires the activation sequence and force intensity of muscles. The EMG sensor 210 is integrated into the inner side of the main body 100, so that after the human body wears the main body 100, the EMG sensor 210 is directly attached to the surface of the human body. Compared with the traditional method of attaching a large number of electrode patches to the human skin, this solution not only omits the cumbersome pasting process, but also reduces the restriction on human movement caused by electrode patches and connecting wires, and can more realistically collect the EMG status of the human body in a natural state.

[0021] For example, the thickness of the body 100 is 0.36 mm, the thickness of the strain sensor 220 is about 1 mm, the thickness of the pressure sensor 240 is ≤3 mm, and the operating temperature range of the strain sensor 220 and the pressure sensor 240 is 15°C to 45°C.

[0022] The control device uses strain sensor 220 to collect the bending and extension angles of the joint, and IMU sensor 230 to collect the joint posture angles and angular velocities. Together, they determine precise joint kinematic data and analyze the limb movement posture. By comparing two sets of joint kinematic data—one for a naked body and one for a body wearing pressure clothing—the control device effectively analyzes the impact of the pressure clothing on the limb movement posture.

[0023] The control device uses pressure sensor 240 to collect pressure distribution data on the body surface. Combined with known body part models and the relationship between pressure and torque, it calculates the external resistance torque generated by the pressure suit on the human body. Simultaneously, using a biomechanical model and based on electromyography (EMG) data collected by EMG sensor 210 before and after wearing the pressure suit, the control device calculates the body's own torque (the net torque required for movement) in the naked state and the wearing torque (the torque required for movement after wearing the pressure suit). The control device determines the difference between the wearing torque and the body's own torque as the external resistance torque generated by the pressure suit. This difference is used as an internal biomechanical reference formed by EMG information to calibrate the accuracy of the external resistance torque, a core parameter for assessing human biomechanical characteristics. By comparing the two sets of detection data—one for the naked state and one for the wearing state—the control device accurately calculates the resistance applied by the pressure suit, effectively analyzing its impact on muscle exertion characteristics.

[0024] This invention breaks through the limitations of traditional measuring equipment, enabling the simultaneous acquisition of motion data and electromyographic signals of the human body in natural activity states, comprehensively and accurately reflecting the dynamic mechanical characteristics of the human body. Furthermore, by collecting full-condition data before and after pressurization of the pressure suit, it analyzes the impact of the pressure suit on the muscle exertion characteristics and limb movement posture, establishing a correlation model between pressure distribution, joint torque, and muscle physiological activity in special pressure suits. This allows for monitoring of dynamic resistance changes during human movement, meeting the long-term dynamic monitoring needs of pressure suits in various scenarios such as research and development and training, and providing scientific data support for the optimized design of special pressure suits.

[0025] For example, the data processing module of the control device analyzes and processes the collected sensor data, and establishes a calculation model of joint motion torque based on mechanical principles and human kinematics models. Simultaneously, considering the complexity of human movement and individual differences, the data processing module optimizes the parameters and performs personalized calibration of the calculation model to improve calculation accuracy. The display screen intuitively presents the analyzed results to the user, showing the changes in joint motion torque with movement, as well as motion characteristic parameters and motion pattern recognition results.

[0026] In some embodiments provided in this application, the electromyography sensor 210 includes a conductive cloth and an elastic element, the elastic element being located between the conductive cloth and the body 100, the elastic element being used to make the conductive cloth adhere to the surface of the human body.

[0027] In this embodiment, the elastic element can be a sponge, and the electromyography sensor 210 adopts a combination of a conductive textile fabric and an elastic element. The pressing pressure of the elastic element makes the conductive fabric fit tightly against the skin surface. The thickness of the elastic element is related to the contact pressure of the conductive fabric. By increasing the thickness of the elastic element, the contact pressure between the skin and the conductive fabric can be strengthened, the contact impedance between the skin and the electromyography sensor 210 can be reduced, the electrical performance can be improved, the electromyography sensor 210 can be prevented from loosening, and the stable acquisition of electromyography signals can be ensured.

[0028] In some embodiments provided in this application, the strain sensor 220 and the pressure sensor 240 are capacitive sensors. The capacitive sensor includes a conductive layer and a dielectric layer, with the dielectric layer located between the two conductive layers.

[0029] In this embodiment, the strain sensor 220 and pressure sensor 240 employ a capacitive three-dimensional stacked structure with high tensile strength and high resolution. After 100 machine washes, the initial capacitance value of the capacitive sensor changes by ≤±2.5%. The capacitive sensor consists of a conductive layer, a dielectric layer, and another conductive layer, with the layers bonded together by an adhesive film. The outer side of the capacitive sensor is encapsulated with an elastic cloth. When the capacitive sensor is under tension or pressure, the area and distance between the two conductive layers change, causing a change in capacitance. The capacitance corresponds to the joint bending angle and pressure, respectively. The capacitive sensor collects the capacitance value when the joint bends or extends or when pressure is applied to the body surface. The control device uses an algorithm to analyze the joint bending angle or force intensity corresponding to the capacitance value, reliably realizing the sensing and detection of joint deformation and body surface pressure.

[0030] In some embodiments provided in this application, the flexible wearable garment 10 further includes: a grounding shielding strip disposed between the IMU sensor 230 and the strain sensor 220, wherein the power supply pin of the IMU sensor 230 is configured with a π-type filter network to suppress power supply ripple.

[0031] In this embodiment, it should be noted that the IMU sensor 230 generates high-frequency digital noise during operation, which can easily interfere with the weak detection signal of the strain sensor 220. By physically isolating the IMU sensor 230 and the strain sensor 220 with a grounded shield, electromagnetic crosstalk can be effectively blocked. Furthermore, the power supply pin of the IMU sensor 230 is configured with a π-type filter network to suppress power supply voltage ripple, reducing high-frequency electromagnetic interference at the source and solving the interference problem of multiple signals at the hardware level.

[0032] For example, the millivolt-level differential signal output by the strain sensor 220 is transmitted using a twisted-pair shielded cable, and the common-mode electromagnetic interference coupled to the twisted-pair shielded cable by the high-frequency oscillation of the IMU sensor 230 is filtered out by an instrumentation amplifier. In addition, the strain sensor 220 is grounded at a single point near the ADC (Analog-to-Digital Converter) to avoid the formation of loops by multiple grounding points and the induction of additional interference.

[0033] In some embodiments provided in this application, the control device is used to calculate the joint attitude angle from the detection data of the IMU sensor 230 using the quaternion method, construct a gravity component compensation model, and remove interference values ​​from the detection data of the strain sensor 220. The control device is also used to apply an adaptive Kalman filter algorithm to reduce noise in the detection data of the strain sensor 220 and perform second-order Butterworth low-pass filtering.

[0034] In this embodiment, the control device constructs an interference compensation mechanism based on attitude calculation at the algorithm level. First, the control device uses the detection data collected by the IMU sensor 230 to calculate the joint attitude angle in real time using the quaternion method. Based on the joint attitude angle, it calculates the spurious deformation effect caused by gravity, constructs a gravity component compensation model, and uses the gravity component compensation model to correct the detection data of the strain sensor 220, eliminating gravity artifact interference caused by attitude deflection and limb movement in the detection data.

[0035] The control device dynamically estimates the noise covariance of the detection system using an adaptive Kalman filter algorithm. Simultaneously, the control device applies a second-order Butterworth low-pass filter with a cutoff frequency of 50Hz to the detection channel of the strain sensor 220, blocking high-frequency noise from the IMU operating frequency band above 100Hz in the frequency domain. This improves the signal-to-noise ratio and measurement accuracy of multi-sensor collaborative operation while maintaining a compact system structure.

[0036] In some embodiments provided in this application, the control device includes: a data acquisition module, which is connected to a flexible sensor via a flexible wire, wherein the elastic modulus of the flexible sensor is lower than that of the flexible wire, and the flexible sensor is connected to the flexible wire via a modulus transition member with a gradually changing modulus gradient.

[0037] In this embodiment, any flexible sensor is connected to the data acquisition module of the control device via a flexible wire. The data acquisition module transmits the detection data acquired by the flexible sensor to the data processing module for processing. The data acquisition module utilizes low-power, high-speed Bluetooth signals for transmission to ensure the stability and accuracy of data transmission.

[0038] The flexible conductors are made of stretchable and bendable materials to ensure stable signal transmission during wearable activities. The wiring of the flexible conductors follows a design principle of avoiding obstructions, ensuring that the conductor path precisely avoids the core sensitive areas of the sensor. This structurally reduces electromagnetic coupling and physical interference, guaranteeing the purity and stability of the sensor signal acquisition.

[0039] The elastic modulus of the flexible sensor is lower than that of the flexible wire. Specifically, the elastic modulus of the strain sensor 220 and the pressure sensor 240 is lower than that of the flexible wire. The strain sensor 220 and the pressure sensor 240 have low elastic modulus in the MPa range and are soft and conform to deformation. The flexible wire has a high elastic modulus in the GPa range, providing good structural support and conductive stability. A functional modulus transition piece with a modulus spanning hundreds of GPa is set between the flexible wire and the flexible sensor to form a continuous and smooth modulus gradient transition. This effectively alleviates the problems of interface stress concentration and deformation mismatch, significantly improves the mechanical stability and conductive reliability of the electrical connection under dynamic conditions, minimizes the risk of poor contact, signal fluctuations, and fatigue failure caused by human movement, and ensures the long-term stable operation of the entire smart wearable system in continuous dynamic use scenarios.

[0040] In some embodiments provided in this application, the body 100 includes an outer fabric and an inner fabric, a strain sensor 220, an IMU sensor 230 and a pressure sensor 240 located between the outer fabric and the inner fabric, an electromyography sensor 210 disposed on the inner side of the inner fabric, and a flexible wire disposed between the outer fabric and the inner fabric.

[0041] In this embodiment, the body 100 uses a double-layer fabric. The outer layer is made of elastic fabric of nylon and spandex, and the inner layer is made of elastic fabric of nylon and spandex, which ensures the elasticity of the body 100 garment while also taking into account the strength and breathability of the fabric.

[0042] The electromyography (EMG) sensor 210 is located on the inside of the inner fabric layer, allowing it to directly contact the skin and ensuring effective data acquisition. The strain sensor 220, IMU sensor 230, and pressure sensor 240, as interlayer sensors, are encapsulated with the flexible wires between the outer and inner fabric layers. This allows the various sensors and circuitry to be arranged separately within the garment's interlayer. The main body 100 provides built-in protection for the flexible sensors, reducing wear and tear and improving the comfort of wearing the flexible wearable garment 10.

[0043] In some embodiments provided in this application, the body 100 further includes: a hot melt mesh film, hot melt mesh films are respectively provided on the opposite side of the outer fabric and the inner fabric, and the flexible sensor is disposed on the body 100 by a hot pressing composite process.

[0044] In this embodiment, when installing the flexible sensor, the outer and inner fabric layers are pre-attached to the breathable hot-melt mesh film, aligning the two hot-melt mesh films inside the body 100 with the fabric side facing outwards. The sandwich sensor is then placed in the interlayer area between the two hot-melt mesh films. A controllable hot-pressing device melts, impregnates, and cross-links the hot-melt mesh film under suitable temperature, pressure, and holding time conditions, achieving a high-strength interface bond between the double-layer fabric and the sandwich sensor while ensuring the fabric's breathability. Simultaneously, the flexible wire and the sandwich sensor are on the same integration level, also placed within the hot-melt mesh interlayer, achieving a flattened and integrated overall structure. This encapsulation method utilizes the hot-pressing composite characteristics of the hot-melt mesh film to fix, seal, isolate, and mechanically cushion the sandwich sensor and flexible wire, effectively improving the structural reliability and operational stability of the sandwich sensor in complex operating environments, providing an efficient and reliable integrated encapsulation solution for the flexible wearable garment 10.

[0045] The electromyography (EMG) sensor 210 is bonded to the inner surface of the inner fabric using a hot-pressing composite process under precise temperature control, achieving seamless integration between the EMG sensor 210 and the main body 100. This hot-pressing composite process ensures continuous and stable contact between the EMG sensor 210 and the human skin while maintaining the original flexibility and wearing comfort of the fabric. Furthermore, the encapsulation properties of the hot-pressing composite effectively isolate external interference such as moisture, improving the stability and signal-to-noise ratio of EMG signal acquisition.

[0046] The main body 100 adopts a hot-pressing composite process that combines a double-layer flexible fabric base with a breathable hot-melt mesh film to achieve integrated packaging of the flexible sensor. This allows the flexible sensor to be highly integrated with the main body 100, enabling it to adapt to repeated bending and movement of the limbs and forming an integrated smart clothing system that combines signal acquisition, structural protection, and wearability.

[0047] In some embodiments provided in this application, such as Figure 1 As shown, flexible sensors are densely deployed in the right upper limb region of the human body, which includes the right upper arm, right forearm, and right palm.

[0048] In this embodiment, the flexible sensors are strategically deployed in the functional areas of the right upper limb. Various flexible sensors are densely arranged in key operational areas such as the right upper arm, forearm, and palm, resulting in a significantly higher sensor density in the right upper limb compared to other areas. Through multi-point collaborative sensing, the force distribution, deformation characteristics, and movement trajectory of the right hand during fine manipulation and complex movements are comprehensively captured. This effectively improves the detection resolution and accuracy of upper limb motion data, providing richer and more precise sensor data support for upper limb motion analysis, force feedback, and interactive control.

[0049] For example, the flexible sensor also includes a temperature sensor 250, which is located on the left side of the human body and is used to detect the temperature of the human body surface to avoid occupying scarce positions on the right side. Furthermore, since the temperatures on the left and right sides of the human body are usually similar, placing the temperature sensor 250 solely on the left side reduces the number of temperature sensors 250 required, improving the uniformity and rationality of the sensor layout relative to the human body.

[0050] In some embodiments provided in this application, such as Figure 1 As shown, IMU sensor 230 is located in the motion areas of the human body, including: the front of the shoulder joint, the back of the shoulder joint, the elbow joint, the hip joint, the thigh, the calf, the ankle joint, the back, the wrist joint, and the hand. Strain sensor 220 and pressure sensor 240 are located in the joint areas of the human body, including: the shoulder, elbow, hip, knee, and ankle.

[0051] In this embodiment, when the human body performs various limb movements, the shoulder, elbow, knee, and ankle joints, as the main force-bearing and deformation hubs, will generate significant structural strain during movement. By clearly defining the placement positions of different types of flexible sensors, joint deformation information can be accurately captured, enabling accurate identification and real-time monitoring of limb movements. Based on the differentiated placement of the flexible sensors according to their detection functions, the IMU sensor 230 covers the main movement areas of the whole body, while the strain and pressure sensor 240 focuses on joint movement areas. This placement method can comprehensively cover the core movement points of the human body, completely and comprehensively capture whole-body movement, deformation, and pressure data, and collect the mechanical and kinematic characteristics during continuous movements, providing reliable data support for the subsequent ergonomic evaluation of pressure suits.

[0052] In one specific embodiment, joint resistance torque tests were conducted on the flexible wearable garment 10 before and after the human body wore the pressure suit. The human body performed typical movements such as shoulder adduction / abduction, elbow flexion / extension, and wrist rotation to verify the feasibility of data acquisition using the flexible wearable garment 10. Taking shoulder abduction as an example, the flexible wearable garment 10 collected and calculated the human body's limb posture, joint angles, and the self-torque of each joint in the naked state (as shown in Table 1), as well as the wearing torque in the pressure suit state, to achieve a quantitative assessment of the quality of shoulder abduction. The experimental results show that the flexible wearable garment 10 can stably capture the mechanical and kinematic characteristics of the shoulder joint in continuous abduction movements, providing reliable data support for further optimization of the flexible wearable garment 10 and ergonomic evaluation of special pressure suits. The control device can provide users with intuitive and effective motion assessment results and personalized suggestions in real time, applicable to various scenarios such as special pressure suit optimization design, sports health assessment, and sports training monitoring, with broad application prospects and social value.

[0053] Table 1

[0054] In this invention, the terms "first," "second," and "third" are used for descriptive purposes only and should not be construed as indicating or implying relative importance; the term "multiple" refers to two or more unless otherwise explicitly defined. The terms "install," "connect," "link," and "fix" should be interpreted broadly. For example, "connect" can be a fixed connection, a detachable connection, or an integral connection; "link" can be a direct connection or an indirect connection through an intermediate medium. Those skilled in the art can understand the specific meaning of the above terms in this invention according to the specific circumstances.

[0055] In the description of this invention, it should be understood that the terms "upper," "lower," "left," "right," "front," "rear," etc., indicate the orientation or positional relationship based on the orientation or positional relationship shown in the accompanying drawings. They are only for the convenience of describing this invention and simplifying the description, and do not indicate or imply that the device or unit referred to must have a specific orientation or be constructed and operated in a specific orientation. Therefore, they should not be construed as limitations on this invention.

[0056] In the description of this specification, the terms "one embodiment," "some embodiments," "specific embodiment," etc., refer to a specific feature, structure, material, or characteristic described in connection with that embodiment or example, which is included in at least one embodiment or example of the present invention. In this specification, the illustrative expressions of the above terms do not necessarily refer to the same embodiment or example. Furthermore, the specific features, structures, materials, or characteristics described may be combined in any suitable manner in one or more embodiments or examples.

[0057] The above are merely some embodiments of the present invention and are not intended to limit the present invention. For those skilled in the art, the present invention can have various modifications and variations. Any modifications, equivalent substitutions, improvements, etc., made within the spirit and principles of the present invention should be included within the protection scope of the present invention.

Claims

1. A flexible wearable garment for measuring compression garment wearing data, characterized in that, include: The main body is worn between the human body and the pressure suit; A flexible sensor is disposed on the body, the flexible sensor comprising: An electromyography (EMG) sensor is used to attach to the surface of the human body to obtain the activation sequence and force intensity of human muscles. A strain sensor, used to detect the bending and stretching angles of human joints; An IMU sensor is used to detect the joint posture angle and angular velocity of human joints; A pressure sensor for detecting pressure on the surface of a human body; The control device, based on the detection data obtained by the flexible sensor when the human body is in a naked state and in a state of wearing the pressure suit, determines the pressure generated by the pressure suit and the influence of the pressure suit on muscle exertion and movement posture.

2. The flexible wearable garment for measuring pressure garment wearing data according to claim 1, characterized in that, The electromyographic sensor includes: A conductive cloth and an elastic element, the elastic element being located between the conductive cloth and the body, the elastic element being used to make the conductive cloth adhere to the surface of the human body.

3. The flexible wearable garment for measuring pressure garment wearing data according to claim 1, characterized in that, The strain sensor and the pressure sensor are capacitive sensors, each comprising a conductive layer and a dielectric layer, wherein the dielectric layer is located between the two conductive layers.

4. The flexible wearable garment for measuring pressure garment wearing data according to claim 1, characterized in that, Also includes: A grounding shield is provided between the IMU sensor and the strain sensor, and the power supply pin of the IMU sensor is configured with a π-type filter network to suppress power supply ripple.

5. The flexible wearable garment for measuring compression garment wearing data according to claim 1, characterized in that, The control device is used to calculate the joint attitude angle from the detection data of the IMU sensor using the quaternion method, construct a gravity component compensation model, and remove interference values ​​from the detection data of the strain sensor. The control device is also used to reduce noise in the detection data of the strain sensor using an adaptive Kalman filter algorithm and to perform second-order Butterworth low-pass filtering.

6. The flexible wearable garment for measuring pressure garment wearing data according to any one of claims 1 to 5, characterized in that, The control device includes: The data acquisition module is connected to the flexible sensor via a flexible wire. The elastic modulus of the flexible sensor is lower than that of the flexible wire. The flexible sensor is connected to the flexible wire via a modulus transition piece with a gradually changing modulus gradient.

7. The flexible wearable garment for measuring pressure garment wearing data according to claim 6, characterized in that, The body includes: The outer fabric and the inner fabric, the strain sensor, the IMU sensor and the pressure sensor are located between the outer fabric and the inner fabric, the electromyography sensor is located on the inner side of the inner fabric, and the flexible wire is located between the outer fabric and the inner fabric.

8. The flexible wearable garment for measuring compression garment wearing data according to claim 7, characterized in that, The body also includes: A hot-melt mesh is provided on one side of the outer fabric and the inner fabric, and on the inner side of the inner fabric. The flexible sensor is disposed on the body through a hot-pressing composite process.

9. The flexible wearable garment for measuring pressure garment wearing data according to any one of claims 1 to 5, characterized in that, The flexible sensors located in the right upper limb region of the human body are densely deployed, and the right upper limb region includes: the right upper arm, the right forearm and the right palm.

10. A flexible wearable garment for measuring compression garment wearing data according to any one of claims 1 to 5, characterized in that, The IMU sensor is located in the motion area of ​​the human body, which includes: the front of the shoulder joint, the back of the shoulder joint, the elbow joint, the hip joint, the thigh, the calf, the ankle joint, the back, the wrist joint, and the hand. The strain sensor and the pressure sensor are located in the joint areas of the human body, including the shoulder, elbow, hip, knee, and ankle.

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