A multi-modal wearable diagnostic system for differentiating between a wave lung injury and a pneumothorax

Abstract

This invention discloses a multimodal wearable diagnostic system for differentiating between pneumothorax and lung injury, belonging to the field of medical devices and military equipment technology. Integrated into the cushioning liner of a bulletproof vest, it includes a flexible carrier, a multimodal sensor array, an adaptive coupling module, and an edge computing control unit. The multimodal sensor array contains sixteen detection nodes, each integrating a flexible microelectromechanical ultrasonic transducer and a bioelectrical impedance electrode. The adaptive coupling module adopts a sandwich structure of a microfluidic airbag layer, a thermal activation control layer, and a solid hydrogel layer, achieving active thermal activation coupling between the sensor and the skin. This invention achieves accurate dual-modal differentiation, solving the problem of traditional methods' difficulty in distinguishing between pneumothorax and pulmonary edema; its integration into the bulletproof vest liner achieves zero parasitic load; and thermal activation coupling and temperature compensation technology ensure stable operation in all weather conditions from -20℃ to 55℃, significantly improving the success rate of combat injury treatment.

Description

Technical Field

[0001] This invention relates to the field of medical devices and military equipment technology, and more specifically, to a multimodal wearable diagnostic system for differentiating between lung injury and pneumothorax. Background Technology

[0003] In modern high-intensity warfare and terrorist attacks, blast waves are one of the main causes of casualties. Blast waves not only cause obvious physical trauma but also lead to the extremely insidious primary blast lung injury (PBI), also known as blast lung.

[0004] The pathological features of blast lung are rupture of alveolar capillaries leading to pulmonary edema and hemorrhage ("wet lung"). The emergency treatment principle is to restrict intravenous fluid administration and provide positive pressure ventilation. Another common combat injury is tension pneumothorax, which is characterized by pleural rupture leading to pneumothorax ("pneumothorax"). The emergency treatment principle is to immediately perform puncture decompression.

[0005] Both present clinically with dyspnea and decreased blood oxygenation, but are extremely difficult to distinguish during traditional physical examinations. Current field emergency care relies on handheld FAST ultrasound, requiring specialized military medics to hold the probe, apply coupling gel, and visually interpret the images. However, this is virtually impossible to accomplish within the crucial "golden ten minutes" of combat, noisy environments, and dim lighting. Furthermore, existing wearable monitoring devices mostly only monitor heart rate and respiration, and cannot perform imaging diagnosis of structural damage within organs. Summary of the Invention

[0006] (a) Technical problems to be solved

[0007] To address the shortcomings of existing technologies, this invention provides a multimodal wearable diagnostic system for differentiating between lung injury and pneumothorax, thus solving the aforementioned problems.

[0008] (II) Technical Solution

[0009] To achieve the above-mentioned objectives, the present invention provides the following technical solution: a multimodal wearable diagnostic system for differentiating between wave lung injury and pneumothorax, comprising: A flexible carrier, wherein the flexible carrier is a plate-like structure that fits the chest and abdomen of the human body, having an inner side and an outer side, and the material of the flexible carrier is a polymer foam material. A multimodal sensing array is disposed on the inner side of the flexible carrier. The multimodal sensing array includes sixteen detection nodes distributed according to human anatomical positions. Each detection node includes a flexible substrate, a flexible microelectromechanical ultrasonic transducer fixed on the flexible substrate, and a bioelectrical impedance electrode. The flexible substrate is made of polyimide and has a thickness of micrometers. An adaptive coupling module is covered on the surface of a multimodal sensing array. The adaptive coupling module includes a microfluidic airbag layer, a thermal activation control layer, and a solid hydrogel layer. The microfluidic airbag layer is located on the outermost side, the thermal activation control layer is located in the middle, and the solid hydrogel layer is located on the innermost side and is in contact with human skin. An edge computing control unit is fixed to the outer side of the flexible carrier. The edge computing control unit is electrically connected to each detection node of the multimodal sensor array through a flexible bus. The edge computing control unit includes a shell, a main control chip housed inside the shell, a memory, a bus interface, a first wireless communication module, and a power management module. The main control chip is a heterogeneous multi-core processor, including an ARM Cortex-M core and a DSP core. An interactive terminal is set independently of the flexible carrier. The interactive terminal includes a housing, a touch screen, a second processor, a second wireless communication module, and an identity recognition module. The touch screen is fixed to the front surface of the housing, and the second processor is electrically connected to the touch screen and the second wireless communication module. Each detection node of the multimodal sensing array is connected to the bus interface of the edge computing control unit via a flexible bus, forming a first communication link; the first wireless communication module of the edge computing control unit and the second wireless communication module of the interactive terminal are connected via radio waves, forming a second communication link.

[0010] Preferably, the flexible bus includes eight parallel flexible conductive fabric wires and a flexible insulating layer covering the eight flexible conductive fabric wires. The flexible conductive fabric wires are made of silver-plated nylon fiber braided tape with a wire width of 2 mm and a wire spacing of 1 mm. The flexible insulating layer is made of thermoplastic polyurethane elastomer with a thickness of 100 micrometers. One end of the flexible bus is fixedly connected to the pads on the flexible substrate of each detection node through anisotropic conductive adhesive, and the other end is connected to the bus interface of the edge computing control unit. The bus interface includes sixteen elastic probes and a clamping cover. The sixteen elastic probes are arranged in two rows. The top of each elastic probe contacts the end of a corresponding flexible conductive fabric wire. The clamping cover uses four screws to press the end of the flexible bus onto the elastic probe. The flexible bus also includes two redundant flexible conductive fabric wires, which are arranged in parallel with the eight parallel wires and are suspended at both ends.

[0011] Preferably, the flexible microelectromechanical ultrasonic transducer of each detection node is a piezoelectric micromechanical ultrasonic transducer chip. The chip has a first operating frequency and a second operating frequency. The first operating frequency is 3MHz and the second operating frequency is 10MHz. The bottom of the chip is fixed to the flexible substrate by a silver paste layer, and the electrodes of the chip are connected to the pads on the flexible substrate by gold wires. The bioelectrical impedance electrode is a ring-shaped conductive fabric electrode, which surrounds the flexible microelectromechanical ultrasonic transducer. The ring-shaped conductive fabric electrode has an inner diameter of 10 mm, an outer diameter of 20 mm, is made of silver-plated nylon fabric, and has a surface resistance of less than 0.5 ohms / square. The ring-shaped conductive fabric electrode is bonded to the flexible substrate with conductive adhesive. Each detection node further includes a node communication module fixed on a flexible substrate. The node communication module includes an impedance matching network, a bandpass filter, a low-noise amplifier, an analog-to-digital converter, and a baseband processor. The input of the impedance matching network is connected to the output of the flexible microelectromechanical ultrasonic transducer. The output of the impedance matching network is connected to the input of the bandpass filter. The output of the bandpass filter is connected to the input of the low-noise amplifier. The output of the low-noise amplifier is connected to the input of the analog-to-digital converter. The output of the analog-to-digital converter is connected to the input of the baseband processor. The output of the baseband processor is connected to a flexible bus.

[0012] Preferably, the impedance matching network consists of two inductors L1 and L2 and a capacitor C1 forming a π-type network, with an input impedance of 3kΩ and an output impedance of 50Ω. The bandpass filter is a fifth-order Butterworth active filter with a passband frequency range of 2MHz to 12MHz and a stopband attenuation greater than 50dB. The low-noise amplifier has an adjustable gain of 20dB to 40dB and a noise figure of less than 1.5dB. The analog-to-digital converter has a sampling rate of 40MHz and a resolution of 12 bits. The baseband processor includes a digital demodulator and a cache controller. The baseband processor is connected to a node cache, which is a DDR3 chip with a capacity of 512MB.

[0013] Preferably, the microfluidic airbag layer includes sixteen airbag units and microchannels. Each airbag unit corresponds to a detection node and is located directly above the detection node. The microchannels connect the sixteen airbag units in series. One end of the microchannel is connected to the outlet of a micro pump. The micro pump is a piezoelectric micro pump, which is fixed to the left shoulder area on the outer side of the flexible carrier. The inlet of the micro pump is connected to the atmosphere through a filter membrane. The thermal activation control layer includes a flexible resistance wire heating film and an electromagnetic shielding foil. The flexible resistance wire heating film is attached to the inner surface of the microfluidic airbag layer. The electromagnetic shielding foil is a copper foil that covers the surface of the flexible resistance wire heating film. The power supply terminal of the flexible resistance wire heating film and the power supply terminal of the micro air pump are connected in parallel to the same drive circuit. The solid hydrogel layer is a sheet-like structure that covers the surface of the flexible microelectromechanical ultrasonic transducer and bioelectrical impedance electrode at all detection nodes. The solid hydrogel layer is made of thermosensitive phase change hydrogel, which softens and undergoes a liquid phase change in the temperature range of 38°C to 40°C. After the phase change, it fills the microscopic depressions in the texture of human skin.

[0014] Preferably, the multimodal sensing array further includes an NTC thermistor array, which consists of sixteen NTC thermistors. Each NTC thermistor is disposed on a flexible substrate adjacent to a detection node. The resistance of the NTC thermistor is 10kΩ at 25°C, and the B value is 3950K. The edge computing control unit also includes a temperature compensation circuit. The input of the temperature compensation circuit is connected to an NTC thermistor array via a flexible bus, and the output of the temperature compensation circuit is connected to the ADC input of the main control chip. The temperature compensation circuit includes a multiplexer, an instrumentation amplifier, an analog-to-digital converter, and a digital signal processor. The sixteen input terminals of the multiplexer are respectively connected to sixteen NTC thermistors. The output terminal of the multiplexer is connected to the input terminal of the instrumentation amplifier. The output terminal of the instrumentation amplifier is connected to the input terminal of the analog-to-digital converter. The output terminal of the analog-to-digital converter is connected to the input terminal of the digital signal processor. The output terminal of the digital signal processor is connected to the main control chip.

[0015] Preferably, the first wireless communication module includes a first UWB RF chip, a first NB-IoT RF chip, and a first RF switch. The first UWB RF chip is of model DW and is connected to a first planar inverted-F antenna. The first NB-IoT RF chip is of model BC and is connected to a first microstrip antenna. The common terminal of the first RF switch is connected to an RF interface of the main control chip, the first output terminal is connected to the input terminal of the first UWB RF chip, and the second output terminal is connected to the input terminal of the first NB-IoT RF chip. The second wireless communication module includes a second UWB RF chip, a second NB-IoT RF chip, and a second RF switch. The second UWB RF chip is model DW1000 and is connected to a second planar inverted-F antenna. The second NB-IoT RF chip is model BC95 and is connected to a second microstrip antenna. The common terminal of the second RF switch is connected to an RF interface of the second processor, the first output terminal is connected to the input terminal of the second UWB RF chip, and the second output terminal is connected to the input terminal of the second NB-IoT RF chip.

[0016] Preferably, the identity recognition module includes an NFC controller, a loop antenna coil, and a security element. The NFC controller is a PN532 and is fixed on a circuit board inside the housing. The loop antenna coil is printed on a flexible circuit board in the peripheral area of ​​the touch screen. The loop antenna coil has 4 turns and a line width of 1mm. The two ends of the loop antenna coil are connected to the antenna interface of the NFC controller. The security element is a SE050 and is connected to the NFC controller via a single-wire protocol. The security element is built into the package of the second processor. The interactive terminal also includes a digital identity card, which is an independent card with an embedded NFC tag chip and a printed antenna. The NFC tag chip stores the injured person's identity information, and the digital identity card communicates with the NFC controller through a loop antenna coil.

[0017] Preferably, it also includes a relay forwarding unit, which is set independently of the flexible carrier and the interactive terminal and fixed to the outer surface of a tactical helmet; The relay unit includes a waterproof housing, a third wireless communication module, a high-gain omnidirectional antenna, and a battery module. The third wireless communication module includes a third UWB RF chip, a third NB-IoT RF chip, and a third RF switch. The third UWB RF chip is connected to the high-gain omnidirectional antenna, the third NB-IoT RF chip is connected to the third microstrip antenna, the common terminal of the third RF switch is connected to the router processor, the first output terminal is connected to the third UWB RF chip, and the second output terminal is connected to the third NB-IoT RF chip. The routing processor is model MT7628 and runs a dynamic source routing protocol. The routing processor is connected to the power output terminal of the battery module. The battery module includes a lithium polymer battery 810 and a battery management chip. The capacity of the lithium polymer battery is 3000mAh.

[0018] Preferably, the flexible carrier has a physical auscultation window at the position corresponding to the left auscultation triangle of the human body. The physical auscultation window is a circular through-hole penetrating the flexible carrier with a diameter of 50 mm. The circular through-hole is covered by a tearable sealing film. The tearable sealing film is made of medical polyurethane film with a thickness of micrometers. The edge of the tearable sealing film is bonded to the inner wall of the circular through-hole by a weakly adhesive medical pressure-sensitive adhesive layer with a peel force of 0.5 N / cm. A pull ring extends from one side of the tearable sealing film. The pull ring is made of the same material as the tearable sealing film and is integrally formed with the tearable sealing film. The edge of the physical auscultation window is also embedded with a flexible near-field communication tag. The flexible near-field communication tag includes a flexible PET substrate, a printed aluminum antenna, and an NFC storage chip. The printed aluminum antenna is printed on the flexible PET substrate. The NFC storage chip is model NTAG213 and is connected to both ends of the printed aluminum antenna. The NFC storage chip stores the device identification number of the edge computing control unit and the summary data of the last three diagnostic results.

[0019] (III) Beneficial Effects

[0020] Compared with the prior art, the present invention provides a multimodal wearable diagnostic system for differentiating between wave lung injury and pneumothorax, which has the following beneficial effects: This multimodal wearable diagnostic system for differentiating between blast wave lung injury and pneumothorax utilizes dual-modal fusion sensing of EIT electrical impedance tomography and PMUT microelectromechanical ultrasound, combined with a spatiotemporal dual-stream neural network algorithm built into the edge computing unit, to achieve accurate differentiation between blast wave lung injury and tension pneumothorax. Pneumothorax is diagnosed when a significant increase in ipsilateral pleural impedance is detected and ultrasound images show the disappearance of the pleural sliding sign; blast wave lung injury is diagnosed when a significant decrease in impedance is detected and ultrasound images show diffuse B-line bursts. This dual-modal verification mechanism effectively solves the problem of single-modal susceptibility to artifact interference, providing medics with clear emergency decision-making basis within the golden ten minutes, avoiding secondary injuries caused by misjudgment, and significantly improving the success rate of combat casualty treatment.

[0021] This multimodal wearable diagnostic system for differentiating lung injury and pneumothorax integrates a multimodal sensor array, an adaptive coupling module, and an edge computing control unit within the cushioning layer of a bulletproof vest. It replaces the original polymer foam or non-Newtonian fluid material liner, achieving zero parasitic weight and adding no extra burden to soldiers. The adaptive coupling module employs a sandwich composite structure, including a microfluidic airbag layer, a thermally activated control layer, and a solid hydrogel layer. Upon detecting an explosive impact or sudden heart rate change, a micro-pump drives the airbag to inflate, providing a vertical pressure of 20-50 mmHg. Simultaneously, a flexible resistance wire heating film heats the solid hydrogel, softening it at 38-40°C and releasing water, instantly filling the skin texture and establishing a stable acoustic and electrical connection. This solves the motion artifacts caused by intense wartime movement and impedance drift in low-temperature environments. The system also integrates an NTC thermistor array and a T-EIT thermistor compensation model, correcting the original EIT impedance data in real time based on skin temperature. This eliminates baseline drift across a wide temperature range of -20°C to 55°C, ensuring stable and reliable operation in all-weather battlefield environments. Attached Figure Description

[0022] Figure 1 This is a schematic diagram of the structure of the present invention; Figure 2 This is a schematic diagram of the flexible carrier structure of the present invention; Figure 3 This is a schematic diagram of the multimodal sensing array structure of the present invention; Figure 4 This is a schematic diagram of the adaptive coupling module structure of the present invention; Figure 5 This is a schematic diagram of the edge computing control unit structure of the present invention; Figure 6 This is a schematic diagram of the flexible bus structure of the present invention; Figure 7 This is a schematic diagram of the relay forwarding unit structure in this invention.

[0023] In the diagram: 100, Flexible carrier; 101, Inner surface; 102, Outer surface; 140, Physical auscultation window; 141, Tearable sealing film; 142, Weakly tacky medical pressure-sensitive adhesive layer; 143, Pull ring; 150, Flexible near-field communication tag; 151, Flexible PET substrate; 152, Printed aluminum antenna; 153, NFC storage chip; 200, Multimodal sensor array; 210, Detection node; 211, Flexible substrate; 212, Flexible MEMS ultrasonic transducer; 213, Bioelectrical impedance electrode; 214, Node communication module; 215, Impedance matching network; 216, Bandpass filter; 217, Low-noise amplifier; 218, Analog-to-digital converter; 219, Baseband. 220, Node buffer; 230, NTC thermistor array; 231, NTC thermistor; 300, Adaptive coupling module; 310, Microfluidic airbag layer; 311, Airbag unit; 312, Microchannel; 313, Micro air pump; 320, Thermal activation control layer; 321, Flexible resistance wire heating film; 322, Electromagnetic shielding foil; 330, Solid hydrogel layer; 400, Edge computing control unit; 401, Housing; 410, Main control chip; 420, Memory; 430, Bus interface; 431, Elastic probe; 432, Pressing cover; 440, First wireless communication module; 441, First UWB RF chip; 442, First NB-IoT 443. RF chip; 444. First RF switch; 445. First planar inverted-F antenna; 450. First microstrip antenna; 460. Power management module; 461. Temperature compensation circuit; 462. Multiplexer; 463. Instrumentation amplifier; 464. Analog-to-digital converter; 465. Digital signal processor; 500. Flexible bus; 510. Flexible conductive fabric wire; 520. Flexible insulating layer; 600. Interactive terminal; 601. Housing; 602. Touch screen; 603. Second processor; 604. Second wireless communication module; 605. Identity recognition module; 606. Second UWB RF chip; 607. Second NB-IoT RF chip; 608. Second RF switch 609. Second Planar Inverted-F Antenna; 610. Second Microstrip Antenna; 611. NFC Controller; 612. Loop Antenna Coil; 613. Security Element; 614. Digital Identity Tag; 615. NFC Tag Chip; 616. Printed Antenna; 800. Relay Unit; 801. Waterproof Housing; 802. Third Wireless Communication Module; 803. High-Gain Omnidirectional Antenna; 804. Battery Module; 805. Third UWB RF Chip; 806. Third NB-IoT RF Chip; 807. Third RF Switch; 808. Third Microstrip Antenna; 809. Router Processor; 810. Lithium Polymer Battery; 811. Battery Management Chip; 900. Tactical Helmet. Detailed Implementation

[0024] The technical solutions of the embodiments of the present invention will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only some embodiments of the present invention, and not all embodiments. Based on the embodiments of the present invention, all other embodiments obtained by those skilled in the art without creative effort are within the scope of protection of the present invention.

[0025] Please see Figures 1-7 The present invention provides a technical solution: A multimodal wearable diagnostic system for differentiating lung injury and pneumothorax includes a flexible carrier 100 made of 8mm thick polyurethane foam, cut to fit the human chest and abdomen in a plate-like shape. The inner surface 101 of the flexible carrier 100 has sixteen detection nodes 210 distributed according to anatomical landmarks (2nd-4th intercostal spaces along the midclavicular line, 5th-7th intercostal spaces along the anterior axillary line, and 8th-10th intercostal spaces along the scapular line). The flexible substrate 211 of each detection node 210 is attached to the inner surface 101 of the flexible carrier 100 using medical pressure-sensitive adhesive. A flexible microelectromechanical ultrasonic transducer 212 and bioelectrical impedance electrodes 213 are fixed on the flexible substrate 211. The flexible microelectromechanical ultrasonic transducer 212 uses a piezoelectric micromechanical ultrasonic transducer chip, the bottom of which is fixed to the flexible substrate 211 by a silver paste layer, and the electrodes are connected to pads on the flexible substrate 211 via gold wires. The bioelectrical impedance electrode 213 is a ring-shaped conductive fabric electrode with an inner diameter of 10 mm and an outer diameter of 20 mm. It surrounds the flexible microelectromechanical ultrasonic transducer 212 and is bonded to the flexible substrate 211 with conductive adhesive.

[0026] An adaptive coupling module 300 covers the surface of the multimodal sensing array 200. Sixteen airbag units 311 of the microfluidic airbag layer 310 are located directly above the sixteen detection nodes 210, and each airbag unit 311 is connected in series via a microchannel 312. One end of the microchannel 312 is connected to the outlet of a micropump 313, which is fixed to the left shoulder region of the outer side 102 of the flexible carrier 100. The flexible resistance wire heating film 321 of the thermal activation control layer 320 is adhered to the inner surface of the microfluidic airbag layer 310, and the electromagnetic shielding foil 322, made of copper foil, covers the surface of the flexible resistance wire heating film 321. The power supply terminal of the flexible resistance wire heating film 321 and the power supply terminal of the micropump 313 are connected in parallel to the same driving circuit. The solid hydrogel layer 330 is a sheet structure that covers the surface of the flexible microelectromechanical ultrasonic transducer 212 and bioelectrical impedance electrode 213 of all detection nodes 210, and the material is a thermosensitive phase change hydrogel.

[0027] The edge computing control unit 400 is fixed to the right rib of the outer side 102 of the flexible carrier 100. The housing 401 internally houses the main control chip 410, memory 420, bus interface 430, first wireless communication module 440, and power management module 450. The main control chip 410 uses a TI AM5728 heterogeneous multi-core processor, including an ARM Cortex-A15 core and a C66x DSP core. The memory 420 includes 2GB of DDR3 SDRAM and 32GB of eMMC flash memory. The bus interface 430 includes sixteen flexible probes 431 and a clamping cover 432.

[0028] The flexible bus 500 includes eight parallel flexible conductive fabric conductors 510 and an external flexible insulating layer 520. The flexible conductive fabric conductors 510 are made of silver-plated nylon fiber braided tape, with a wire width of 2 mm and a wire spacing of 1 mm. The flexible insulating layer 520 is made of thermoplastic polyurethane elastomer with a thickness of 100 μm. The flexible bus 500 also includes two redundant flexible conductive fabric conductors 510, arranged parallel to the eight parallel conductors and suspended at both ends. One end of the flexible bus 500 is fixedly connected to the pads on the flexible substrate 211 of each detection node 210 using anisotropic conductive adhesive, and the other end is pressed against the elastic probe 431 by a clamping cover plate 432.

[0029] The interactive terminal 600 is a ruggedized handheld device, with its housing 601 made of magnesium alloy. The touchscreen display 602 is a 5.5-inch AMOLED screen with a resolution of 1920×1080, covered with anti-reflective glass. The second processor 603 uses a Qualcomm Snapdragon 660 chip. The second wireless communication module 604 includes a second UWB RF chip 606 and a second NB-IoT RF chip 607. The identity recognition module 605 includes an NFC controller 611, a loop antenna coil 612, and a security element 613. The loop antenna coil 612 is printed on a flexible circuit board around the touchscreen display 602, with 4 turns and a line width of 1mm.

[0030] The relay unit 800 is fixed to the outer surface of the tactical helmet 900. The waterproof housing 801 houses a third wireless communication module 802, a high-gain omnidirectional antenna 803, and a battery module 804. The third wireless communication module 802 includes a third UWB RF chip 805, a third NB-IoT RF chip 806, and a third RF switch 807. The routing processor 809 uses an MT7628 chip and runs a dynamic source routing protocol. The battery module 804 includes a 3000mAh lithium polymer battery 810 and a battery management chip 811.

[0031] When the inertial measurement unit (integrated within the main control chip 410) detects an acceleration value exceeding 5G, the main control chip 410 generates a high-priority acquisition command. This command is broadcast to all detection nodes 210 via the flexible bus 500. Simultaneously, the drive circuit activates the micro air pump 313 and the flexible resistance wire heating film 321. The micro air pump 313 inflates sixteen airbag units 311 through the microfluidic channel 312, and within 2 seconds, the airbag units 311 expand to a pressure of 30 mmHg, pressing the detection nodes 210 against the human skin. The flexible resistance wire heating film 321 heats up at a rate of 5℃ / s, heating the solid hydrogel layer 330 to 39℃. The solid hydrogel layer 330 softens upon heating and releases trace amounts of moisture, filling the skin texture and completing the acoustic and electrical coupling.

[0032] Upon receiving the synchronization trigger frame, the baseband processor 219 of each detection node 210 latches the node clock and adjusts the sampling start time to achieve microsecond-level synchronization. The flexible microelectromechanical ultrasonic transducer 212 emits ultrasonic waves and receives echo signals. These signals are processed sequentially through an impedance matching network 215, a bandpass filter 216, a low-noise amplifier 217, and an analog-to-digital converter 218, before being stored in the node buffer 220 by the baseband processor 219. The impedance signals collected by the bioelectrical impedance electrode 213 are also processed and stored in the node buffer 220. Within their allocated TDMA time slots, each detection node 210 transmits its buffered data to the bus interface 430 of the edge computing control unit 400 via the flexible bus 500.

[0033] After receiving data, the main control chip 410 of the edge computing control unit 400 first corrects the impedance data based on the skin temperature detected by the NTC thermistor 231 through the temperature compensation circuit 460. The corrected data is then input into the trauma identification algorithm stored in the memory 420 to extract the EIT impedance distribution map and ultrasound image features. When the ipsilateral pleural impedance value is detected to be higher than the first threshold and the ultrasound image shows the disappearance of the pleural sliding sign, a pneumothorax judgment signal is generated; when the ipsilateral pleural impedance value is detected to be lower than the second threshold and the ultrasound image shows the outbreak of diffuse vertical comet tail sign, an explosive shock wave lung injury judgment signal is generated.

[0034] The edge computing control unit 400 transmits raw ultrasound radio frequency data and diagnostic results to the interactive terminal 600 via the UWB mode of the first wireless communication module 440. The touch screen 602 of the interactive terminal 600 displays the diagnostic conclusions and suggested first aid measures. Simultaneously, the digital identification tag 614 communicates with the NFC controller 611 via the loop antenna coil 612, associating and storing the injured person's identification information with the diagnostic data in the secure element 613. When the injured person needs to be evacuated, the detachable digital identification transfer module connects to the edge computing control unit 400 via the magnetic interface 704, synchronously storing the injured person's identification information, vital signs data, and diagnostic image snapshots, supporting NFC wireless reading.

[0035] Example 2: In this embodiment, the structures of the flexible carrier 100, multimodal sensor array 200, adaptive coupling module 300, and edge computing control unit 400 are basically the same as in Embodiment 1. The difference lies in the communication mode and emergency backup mechanism between the interactive terminal 600 and the edge computing control unit 400.

[0036] When electronic interference exists on the battlefield or the distance between the edge computing control unit 400 and the interactive terminal 600 exceeds 50 meters, the first radio frequency switch 443 of the first wireless communication module 440 automatically switches to the second output terminal, the first NB-IoT radio frequency chip 442 is activated, and data is transmitted in NB-IoT mode through the first microstrip antenna 445. Simultaneously, the second radio frequency switch 608 of the second wireless communication module 604 switches to the second output terminal, and the second NB-IoT radio frequency chip 607 receives data. In this mode, the main control chip 410 of the edge computing control unit 400 first inputs the raw ultrasonic radio frequency data into the data compression coprocessor (integrated within the main control chip 410) for compression. The compressed data volume is reduced to 1 / 10 of the original data and transmitted to the interactive terminal 600 via the NB-IoT network. The interactive terminal 600 receives the data, decompresses it, and displays the diagnostic conclusion.

[0037] When the distance between the edge computing control unit 400 and the interactive terminal 600 exceeds the coverage area of ​​the NB-IoT network (e.g., in a tunnel or basement), the relay unit 800 is activated. The routing processor 809 runs a dynamic source routing protocol, scanning for available relay nodes in the vicinity. The third radio frequency switch 807 of the third wireless communication module 802 switches to the appropriate channel according to routing instructions, receives the signal emitted by the edge computing control unit 400 through the high-gain omnidirectional antenna 803, and forwards it to the interactive terminal 600. The battery module 804 of the relay unit 800 can operate continuously for 72 hours, ensuring uninterrupted communication links.

[0038] The human-computer interface of the interactive terminal 600 has a blind-zone forced confirmation mechanism. When the edge computing control unit 400 determines that the scan result of the torso region is normal, it sends a lock signal to the interactive terminal 600 through the second communication link. After receiving the signal, the second processor 603 of the interactive terminal 600 outputs a high level to the gate of the field-effect transistor 605 of the locking switch circuit 604. The field-effect transistor 605 conducts, the coil of the relay 606 is energized, the normally open contact closes, the power supply circuit of the confirmation button 623 is connected, and the confirmation button 623 is in an operable state. At the same time, the graphical user interface 620 on the touch screen 602 highlights the limb region icon 622. After the medic examines the wounded's limbs, he touches the limb region icon 622. After the second processor 603 detects the touch command, it maintains the high level of the gate of the field-effect transistor 605, and the confirmation button 623 remains operable. After the medic clicks the confirmation button 623, the system generates a complete diagnostic report including the status of the torso and limbs.

[0039] The flexible carrier 100 has a physical auscultation window 140 located at the position corresponding to the left auscultation triangle of the human body. This window is a circular through-hole with a diameter of 50 mm, covered by a tearable sealing film 141. The tearable sealing film 141 is made of a 50 μm thick medical polyurethane film, and its edges are adhered to the inner wall of the circular through-hole by a weakly adhesive medical pressure-sensitive adhesive layer 142, with a peel force of 0.5 N / cm. A pull ring 143 extends from one side of the tearable sealing film 141 and is integrally formed with the tearable sealing film 141. When the electronic system completely fails (such as when the battery is depleted or the main control chip is damaged), the medic can pull the pull ring 143 to tear open the tearable sealing film 141, expose the wounded's skin, and perform physical auscultation using a traditional stethoscope.

[0040] A flexible near-field communication (NFC) tag 150 is embedded in the edge of the physical auscultation window 140. This tag includes a flexible PET substrate 151, a printed aluminum antenna 152, and an NFC storage chip 153. The NFC storage chip 153, model NTAG213, is connected to both ends of the printed aluminum antenna 152. The NFC storage chip 153 stores the device identification number of the edge computing control unit 400 and summary data (including timestamps, impedance averages, etc.) of the last three diagnostic results. When the electronic system fails and historical diagnostic information is needed, the medic can use an NFC-enabled mobile phone to approach the flexible NFC tag 150 and read the stored diagnostic summary as a reference for subsequent treatment.

[0041] The digital identity transfer module is fixed to the outer surface 102 of the flexible carrier 100 using a snap-fit ​​705. The independent housing 701 of the digital identity transfer module 700 houses a storage chip 702, an NFC antenna 703, and an encryption coprocessor 706. The encryption coprocessor 706 incorporates an SM4 encryption algorithm unit to encrypt the wounded soldier's identity information, vital signs data, and diagnostic image snapshots stored in the storage chip 702. When the wounded soldier is transported to the field hospital, medical personnel approach the digital identity transfer module 700 using an NFC reader. The encryption coprocessor 706 decrypts the data and outputs it, ensuring data security during transport.

[0042] The foregoing has shown and described the basic principles, main features, and advantages of the present invention. Those skilled in the art should understand that the present invention is not limited to the above embodiments. The embodiments and descriptions in the specification are merely preferred examples and are not intended to limit the invention. Various changes and modifications can be made to the invention without departing from its spirit and scope, and all such changes and modifications fall within the scope of the present invention as claimed. The scope of protection of the present invention is defined by the appended claims and their equivalents.

Claims

1. A multimodal wearable diagnostic system for differentiating between lung injury and pneumothorax, characterized in that, include: The flexible carrier (100) is a plate-like structure that fits the chest and abdomen of the human body, and has an inner side (101) and an outer side (102). The flexible carrier (100) is made of polymer foam material. A multimodal sensing array (200) is disposed on the inner side (101) of the flexible carrier (100). The multimodal sensing array (200) includes sixteen detection nodes (210) distributed according to human anatomical positions. Each detection node (210) includes a flexible substrate (211), a flexible microelectromechanical ultrasonic transducer (212) fixed on the flexible substrate (211), and a bioelectrical impedance electrode (213). The flexible substrate (211) is made of polyimide and has a thickness of 50 micrometers. An adaptive coupling module (300) is covered on the surface of a multimodal sensing array (200). The adaptive coupling module (300) includes a microfluidic airbag layer (310), a thermal activation control layer (320), and a solid hydrogel layer (330). The microfluidic airbag layer (310) is located on the outermost side, the thermal activation control layer (320) is located in the middle, and the solid hydrogel layer (330) is located on the innermost side and is in contact with human skin. An edge computing control unit (400) is fixed to the outer side (102) of the flexible carrier (100). The edge computing control unit (400) is electrically connected to each detection node (210) of the multimodal sensing array (200) through a flexible bus (500). The edge computing control unit (400) includes a housing (401), a main control chip (410) housed inside the housing (401), a memory (420), a bus interface (430), a first wireless communication module (440), and a power management module (450). The main control chip (410) is a heterogeneous multi-core processor, including an ARM Cortex-M core and a DSP core. An interactive terminal (600) is set independently of the flexible carrier (100). The interactive terminal (600) includes a housing (601), a touch screen (602), a second processor (603), a second wireless communication module (604), and an identity recognition module (605). The touch screen (602) is fixed to the front surface of the housing (601). The second processor (603) is electrically connected to the touch screen (602) and the second wireless communication module (604). Each detection node (210) of the multimodal sensing array (200) is connected to the bus interface (430) of the edge computing control unit (400) via a flexible bus (500) to form a first communication link; the first wireless communication module (440) of the edge computing control unit (400) and the second wireless communication module (604) of the interactive terminal (600) are connected via radio waves to form a second communication link.

2. The multi-modal wearable diagnostic system for differentiating between lung contusion and pneumothorax according to claim 1, wherein, The flexible bus (500) includes eight parallel flexible conductive fabric wires (510) and a flexible insulating layer (520) covering the outside of the eight flexible conductive fabric wires (510). The flexible conductive fabric wires (510) are made of silver-plated nylon fiber braided tape with a wire width of 2 mm and a wire spacing of 1 mm. The flexible insulating layer (520) is made of thermoplastic polyurethane elastomer with a thickness of 100 micrometers. One end of the flexible bus (500) is fixedly connected to the pads on the flexible substrate (211) of each detection node (210) by anisotropic conductive adhesive, and the other end is connected to the bus interface (430) of the edge computing control unit (400). The bus interface (430) includes sixteen elastic probes (431) and a clamping cover plate (432). The sixteen elastic probes (431) are arranged in two rows. The top of each elastic probe (431) contacts the end of a corresponding flexible conductive fabric wire (510). The clamping cover plate (432) clamps the end of the flexible bus (500) onto the elastic probe (431) with four screws. The flexible bus (500) also includes two redundant flexible conductive fabric wires (510), which are arranged in parallel with the eight parallel wires and are suspended at both ends.

3. The multi-modal wearable diagnostic system for differentiating between lung contusion and pneumothorax according to claim 2, wherein, Each of the detection nodes (210) has a flexible microelectromechanical ultrasonic transducer (212) which is a piezoelectric micromechanical ultrasonic transducer chip. The chip has a first operating frequency and a second operating frequency. The first operating frequency is 3MHz and the second operating frequency is 10MHz. The bottom of the chip is fixed to the flexible substrate (211) by a silver paste layer. The electrodes of the chip are connected to the pads on the flexible substrate (211) by gold wires. The bioelectrical impedance electrode (213) is a ring-shaped conductive fabric electrode, which surrounds the flexible microelectromechanical ultrasonic transducer (212). The ring-shaped conductive fabric electrode has an inner diameter of 10 mm, an outer diameter of 20 mm, is made of silver-plated nylon fabric, and has a surface resistance of less than 0.5 ohms / square. The ring-shaped conductive fabric electrode is bonded to the flexible substrate (211) with conductive adhesive. Each of the detection nodes (210) further includes a node communication module (214), which is fixed on a flexible substrate (211) and includes an impedance matching network (215), a bandpass filter (216), a low-noise amplifier (217), an analog-to-digital converter (218), and a baseband processor (219). The input of the impedance matching network (215) is connected to the output of the flexible microelectromechanical ultrasonic transducer (212), the output of the impedance matching network (215) is connected to the input of the bandpass filter (216), the output of the bandpass filter (216) is connected to the input of the low-noise amplifier (217), the output of the low-noise amplifier (217) is connected to the input of the analog-to-digital converter (218), the output of the analog-to-digital converter (218) is connected to the input of the baseband processor (219), and the output of the baseband processor (219) is connected to the flexible bus (500).

4. The multi-modal wearable diagnostic system for differentiating between lung contusion and pneumothorax according to claim 3, wherein, The impedance matching network (215) consists of two inductors L1 and L2 and a capacitor C1 forming a π-type network. The input impedance of the π-type network is 3kΩ and the output impedance is 50Ω. The bandpass filter (216) is a fifth-order Butterworth active filter with a passband frequency range of 2MHz to 12MHz and a stopband attenuation greater than 50dB. The low-noise amplifier (217) has an adjustable gain of 20dB to 40dB and a noise figure of less than 1.5dB. The analog-to-digital converter (218) has a sampling rate of 40MHz and a resolution of 12bit; The baseband processor (219) includes a digital demodulator and a cache controller. The baseband processor (219) is connected to a node cache (220), which is a DDR3 chip with a capacity of 512MB.

5. The multi-modal wearable diagnostic system for differentiating between a wave lung injury and a pneumothorax according to claim 4, wherein, The microfluidic airbag layer (310) includes sixteen airbag units (311) and microchannels (312). Each airbag unit (311) corresponds to a detection node (210) and is located directly above the detection node (210). The microchannels (312) connect the sixteen airbag units (311) in series. One end of the microchannels (312) is connected to the outlet of a micro air pump (313). The micro air pump (313) is a piezoelectric micro air pump, which is fixed to the left shoulder area of ​​the outer side (102) of the flexible carrier (100). The inlet of the micro air pump (313) is connected to the atmosphere through a filter membrane. The thermal activation control layer (320) includes a flexible resistance wire heating film (321) and an electromagnetic shielding foil (322). The flexible resistance wire heating film (321) is attached to the inner surface of the microfluidic airbag layer (310). The electromagnetic shielding foil (322) is a copper foil that covers the surface of the flexible resistance wire heating film (321). The power supply terminal of the flexible resistance wire heating film (321) and the power supply terminal of the micro air pump (313) are connected in parallel to the same driving circuit. The solid hydrogel layer (330) is a sheet structure that covers the surface of the flexible microelectromechanical ultrasonic transducer (212) and bioelectrical impedance electrode (213) of all detection nodes (210). The solid hydrogel layer (330) is made of thermosensitive phase change hydrogel. The thermosensitive phase change hydrogel softens and undergoes liquid phase change in the temperature range of 38°C to 40°C. After the phase change, it fills the microscopic depressions in the texture of human skin.

6. The multimodal wearable diagnostic system for differentiating lung injury and pneumothorax according to claim 5, characterized in that, The multimodal sensing array (200) also includes an NTC thermistor array (230), which consists of sixteen NTC thermistors (231). Each NTC thermistor (231) is disposed on a flexible substrate (211) adjacent to a detection node (210). The resistance value of the NTC thermistor (231) is 10kΩ at 25°C, and the B value is 3950K. The edge computing control unit (400) also includes a temperature compensation circuit (460). The input terminal of the temperature compensation circuit (460) is connected to the NTC thermistor array (230) via a flexible bus (500), and the output terminal of the temperature compensation circuit (460) is connected to the ADC input terminal of the main control chip (410). The temperature compensation circuit (460) includes a multiplexer (461), an instrumentation amplifier (462), an analog-to-digital converter (463), and a digital signal processor (464). The sixteen input terminals of the multiplexer (461) are respectively connected to sixteen NTC thermistors (231). The output terminal of the multiplexer (461) is connected to the input terminal of the instrumentation amplifier (462). The output terminal of the instrumentation amplifier (462) is connected to the input terminal of the analog-to-digital converter (463). The output terminal of the analog-to-digital converter (463) is connected to the input terminal of the digital signal processor (464). The output terminal of the digital signal processor (464) is connected to the main control chip (410).

7. The multimodal wearable diagnostic system for differentiating between lung injury and pneumothorax according to claim 6, characterized in that, The first wireless communication module (440) includes a first UWB radio frequency chip (441), a first NB-IoT radio frequency chip (442), and a first radio frequency switch (443). The first UWB radio frequency chip (441) is model DW1000 and is connected to a first planar inverted F antenna (444). The first NB-IoT radio frequency chip (442) is model BC95 and is connected to a first microstrip antenna (445). The common terminal of the first radio frequency switch (443) is connected to a radio frequency interface of the main control chip (410). The first output terminal is connected to the input terminal of the first UWB radio frequency chip (441), and the second output terminal is connected to the input terminal of the first NB-IoT radio frequency chip (442). The second wireless communication module (604) includes a second UWB RF chip (606), a second NB-IoT RF chip (607), and a second RF switch (608). The second UWB RF chip (606) is a DW1000 and is connected to a second planar inverted-F antenna (609). The second NB-IoT RF chip (607) is a BC95 and is connected to a second microstrip antenna (610). The common terminal of the second RF switch (608) is connected to an RF interface of the second processor (603). The first output terminal is connected to the input terminal of the second UWB RF chip (606), and the second output terminal is connected to the input terminal of the second NB-IoT RF chip (607).

8. The multimodal wearable diagnostic system for differentiating between lung injury and pneumothorax according to claim 7, characterized in that, The identity recognition module (605) includes an NFC controller (611), a loop antenna coil (612), and a security element (613). The NFC controller (611) is a PN532 and is fixed on a circuit board inside the housing (601). The loop antenna coil (612) is printed on a flexible circuit board in the peripheral area of ​​the touch screen (602). The loop antenna coil (612) has 4 turns and a line width of 1mm. The two ends of the loop antenna coil (612) are connected to the antenna interface of the NFC controller (611). The security element (613) is a SE050 and is connected to the NFC controller (611) via a single-wire protocol. The security element (613) is built into the package of the second processor (603). The interactive terminal (600) also includes a digital identity card (614), which is an independent card with an embedded NFC tag chip (615) and a printed antenna (616). The NFC tag chip (615) stores the injured person's identity information. The digital identity card (614) communicates with the NFC controller (611) through a loop antenna coil (612). 9.The multi-modal wearable diagnostic system for differentiating between a wave lung injury and a pneumothorax according to claim 8, wherein, It also includes a relay forwarding unit (800), which is set independently of the flexible carrier (100) and the interactive terminal (600) and is fixed to the outer surface of a tactical helmet (900); The relay unit (800) includes a waterproof housing (801), a third wireless communication module (802), a high-gain omnidirectional antenna (803), and a battery module (804). The third wireless communication module (802) includes a third UWB RF chip (805), a third NB-IoT RF chip (806), and a third RF switch (807). The third UWB RF chip (805) is connected to the high-gain omnidirectional antenna (803), the third NB-IoT RF chip (806) is connected to the third microstrip antenna (808), the common terminal of the third RF switch (807) is connected to the routing processor (809), the first output terminal is connected to the third UWB RF chip (805), and the second output terminal is connected to the third NB-IoT RF chip (806). The routing processor (809) is model MT7628 and runs a dynamic source routing protocol. The routing processor (809) is connected to the power output terminal of the battery module (804). The battery module (804) includes a lithium polymer battery (810) and a battery management chip (811). The lithium polymer battery (810) has a capacity of 3000mAh.

10. The multi-modal wearable diagnostic system for differentiating between a wave lung injury and a pneumothorax of claim 9, wherein, The flexible carrier (100) has a physical auscultation window (140) at the position corresponding to the auscultation triangle area on the left side of the human body. The physical auscultation window (140) is a circular through hole penetrating the flexible carrier (100) with a diameter of 50mm. The circular through hole is covered by a tearable sealing film (141), which is made of medical polyurethane film with a thickness of 50 micrometers. The edge of the tearable sealing film (141) is bonded to the inner wall of the circular through hole by a weakly adhesive medical pressure-sensitive adhesive layer (142), and the peel force of the weakly adhesive medical pressure-sensitive adhesive layer (142) is 0.5 N / cm. A pull ring (143) extends from one side of the tearable sealing film (141). The pull ring (143) is made of the same material as the tearable sealing film (141) and is integrally formed with the tearable sealing film (141). The edge of the physical auscultation window (140) is also embedded with a flexible near-field communication tag (150). The flexible near-field communication tag (150) includes a flexible PET substrate (151), a printed aluminum antenna (152), and an NFC storage chip (153). The printed aluminum antenna (152) is printed on the flexible PET substrate (151). The NFC storage chip (153) is model NTAG213 and is connected to both ends of the printed aluminum antenna (152). The NFC storage chip (153) stores the device identification number of the edge computing control unit (400) and the summary data of the last three diagnostic results.

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