Skin operation scar prevention and nursing device based on intelligent temperature control

Abstract

The invention relates to the technical field of medical apparatus and instruments, and discloses a skin operation scar prevention and nursing device based on intelligent temperature control, which comprises a soft shell, a temperature conduction plate and a temperature adjusting assembly. A wound inflammation early warning and partition targeting temperature control system based on a thermal image matrix is arranged in the temperature conduction plate, a pulse type zero-energy-consumption endurance management strategy system based on PCM latent heat state observation is arranged in the temperature adjusting assembly, and the inner side of the soft shell is fixedly connected with an air bag and a scale temperature conduction array. Skin contact surface array temperature data are collected through the flexible temperature measurement array layer, the partition logic control circuit independently regulates and controls the current on-off states of different areas, and targeted cooling of an inflammation area and hot compress of a normal area are achieved. The latent heat characteristic of the solid-liquid phase change composite material is matched with a logic judgment circuit to control the start and stop of active equipment, so that pulse type zero-energy-consumption operation is realized; the air bag drives the medical silica gel layer to be attached to the limb, and the heat conduction efficiency and the wearing comfort are improved in cooperation with the scale structure.

Description

Technical Field

[0001] This invention relates to the field of medical device technology, specifically to a skin surgical scar prevention and care device based on intelligent temperature control. Background Technology

[0002] Post-operative scar prevention and care are crucial for patients' cosmetic restoration and functional recovery. Clinical studies have shown that physical temperature control interventions can regulate local blood circulation and collagen metabolism, thereby inhibiting scar hyperplasia.

[0003] Current skin care devices generally employ uniform heating and cooling modes. Surgical incision healing processes exhibit spatial variability; some areas are in the acute inflammatory phase with pathologically high temperatures, while surrounding areas are in the proliferative and remodeling phase requiring heat to promote metabolism. Traditional uniform temperature control methods cannot simultaneously address the physiological needs of different lesion areas. Continuous heating of inflamed areas exacerbates tissue damage, while excessive cooling of proliferative areas delays healing. There is a lack of targeted, zoned, independent temperature control mechanisms.

[0004] Current portable temperature-controlled nursing devices primarily rely on battery-powered active cooling components for continuous thermal management. The continuous high-load operation of these active components leads to rapid energy consumption and short device runtime, failing to meet patients' needs for prolonged continuous use. Existing technologies fail to effectively utilize the latent heat storage characteristics of phase change materials for passive, coordinated temperature control and lack intelligent energy management strategies, resulting in low energy efficiency.

[0005] Traditional nursing devices often employ flat, rigid structures or single-layer flexible structures for their contact surfaces. The human limb surface is mostly irregularly curved, making it difficult for traditional structures to achieve a tight fit. This results in an air insulation layer between the device and the skin, reducing heat conduction efficiency. Rigid components can easily generate localized high-pressure points during limb movement, causing physical pressure damage to newly formed, delicate skin. Furthermore, the lack of effective antibacterial and breathable mechanisms increases the risk of wound infection. Summary of the Invention

[0006] To address the shortcomings of existing technologies, this invention provides a skin surgical scar prevention and care device based on intelligent temperature control. It solves the problems of existing care devices that use a uniform temperature control mode, which cannot take into account the differentiated thermal management needs of different wound healing stages, leading to aggravated local inflammation; rely solely on continuous operation of active equipment, resulting in low energy utilization and short battery life; and have contact structures that are difficult to fit closely to the irregular curved surfaces of the human body, resulting in low heat conduction efficiency and pressure damage.

[0007] To achieve the above objectives, the present invention is implemented through the following technical solution: a skin surgical scar prevention and care device based on intelligent temperature control, comprising a soft shell, a temperature conduction plate fixedly connected to the inner side of the bottom of the soft shell, connecting shells fixedly connected to the outer sides of both ends of the soft shell, a filter air-cooling component provided on the inner side of both connecting shells, and a temperature regulating component provided between the soft shell and the temperature conduction plate.

[0008] The temperature conduction plate internally houses a wound inflammation early warning and zoned targeted temperature control system based on a thermal imaging matrix. This system is configured to collect array temperature data of the skin contact surface and output independent temperature control commands for different areas. The system includes a flexible temperature sensing array layer embedded within the internal interlayer of the temperature conduction plate. This layer contains multiple miniature temperature sensors arranged according to a preset row and column rule, used to sense and output real-time temperature signals from the temperature conduction plate contact surface. The system also includes a zoned logic control circuit. Its signal input terminals are connected one-to-one with the multiple miniature temperature sensors, and its control output terminals are electrically connected to multiple power transmission boards. The zoned logic control circuit is configured to store the mapping relationship between sensor coordinates and power transmission board positions, and based on whether the temperature signals fed back by the miniature temperature sensors exceed a preset threshold, it generates targeted control signals to switch the current on / off state of the corresponding area's power transmission board.

[0009] The temperature regulation component internally incorporates a pulsed zero-energy endurance management strategy system based on PCM latent heat state observation. This system is configured to monitor the phase change plateau state of the internal phase change material and control the start and stop power supply of the temperature regulation component. The system includes a phase change energy storage encapsulation unit filled within the soft shell and located in the gap of the temperature regulation component. The phase change energy storage encapsulation unit is filled with a solid-liquid phase change composite material, and its inner wall is provided with an elastic buffer structure. This elastic buffer structure is a compression deformation layer fitted to the inner wall, configured to generate a backward elastic displacement under internal pressure to provide space for the volume expansion of the solid-liquid phase change composite material. The system also includes a differential temperature monitoring component, comprising a core temperature probe fixed at the geometric center of the solid-liquid phase change composite material and an interface temperature probe fixed at the outer boundary of the phase change energy storage encapsulation unit. Both the core temperature probe and the interface temperature probe are connected to a logic judgment circuit. The logic judgment circuit is configured to calculate the real-time temperature difference between the core temperature probe and the interface temperature probe, and determine whether the solid-liquid phase change composite material is in an isothermal endothermic stage based on the real-time temperature difference value and the rate of change.

[0010] The temperature control assembly includes multiple power supply boards, all fixedly connected to the inner top of the flexible housing. Multiple heating wires are housed inside the flexible housing, and the power supply boards are fixedly connected to the input ends of the heating wires. Protective flexible plates are fixedly connected to both sides of the flexible housing, and temperature guide plates are fixedly connected between two protective flexible plates. These temperature guide plates are located on the outer sides of the heating wires. The temperature control assembly also includes a water tank, fixedly connected to the inner side of the flexible housing. A water pump is fixedly connected to the inner side of the water tank, and a water circulation pipe is fixedly connected to the output end of the water pump. The other end of the water circulation pipe is fixedly connected to the inner side of the water tank, and the water circulation pipe is also fixedly connected to the inner side of the temperature guide plates.

[0011] The air-cooled filter assembly includes a connecting shell, which is fixedly connected to the inside of a flexible shell. Multiple dustproof inclined plates are fixedly connected to the inner side of the end of the connecting shell. Two filter plates are fixedly connected to the inner side of the connecting shell. Multiple connecting channels are provided at one end of the flexible shell near the connecting shell. A fan housing is fixedly connected to the inner side of the end of the flexible shell and is fixedly connected to the connecting channels. The air-cooled filter assembly also includes multiple brackets, which are fixedly connected to the inside of the fan housing. A dustproof plate is fixedly connected to one end of the fan housing, and multiple filter plates are fixedly connected to the inner side of the other end of the fan housing. Fans are installed inside each of the brackets.

[0012] An airbag is fixedly connected to the bottom outer side of the temperature conduction plate. Two air pumps inside both ends of the soft shell are also fixedly connected to the connection channel. The output ends of multiple air pumps are fixedly connected between the temperature conduction plate and the airbag. A nano-silver antibacterial layer is fixedly connected to the outside of the airbag. A medical silicone layer is fixedly connected to the outside of the nano-silver antibacterial layer. Both the medical silicone layer and the nano-silver antibacterial layer are fixedly connected to the outside of the temperature conduction plate. Multiple scale temperature conduction arrays are set between the medical silicone layer and the nano-silver antibacterial layer. Temperature probes are fixedly set between the multiple scale temperature conduction arrays. Multiple temperature probes are also set between the medical silicone layer and the nano-silver antibacterial layer.

[0013] Preferably, a multi-media integrated coupling interface module is fixedly connected to the outer side of the middle part of the soft shell. A connecting wire is fixedly connected to the connecting end of the multi-media integrated coupling interface module. A display controller is fixedly connected to the connecting end of the connecting wire. A lint hook is fixedly connected to the outer side of one end of the soft shell. A lint adhesive tape is fixedly connected to the outer side of the other end of the soft shell. The lint hook is attached to the outer side of the lint adhesive tape.

[0014] This invention provides a skin surgical scar prevention and care device based on intelligent temperature control. It has the following beneficial effects:

[0015] 1. This invention utilizes the coordinated operation of an airbag, a medical silicone layer, and a scale-like temperature conduction array. An air pump drives the airbag to expand, generating flexible pressure that pushes the medical silicone layer to tightly conform to the irregular contours of the limb, eliminating air gaps at the heat transfer interface. The scale-like temperature conduction array, with its biomimetic multi-unit structure, maintains a continuous heat conduction pathway during limb bending and deformation. Combined with the release of silver ions from the nano-silver antibacterial layer to inhibit bacterial growth, this invention creates a stable, uniformly heat-transmitting, and sterile wound healing microenvironment.

[0016] 2. This invention establishes a wound inflammation early warning and zoned targeted temperature control system based on a thermal imaging matrix. It utilizes a flexible temperature measurement array layer embedded in the internal interlayer of a temperature conduction plate to collect two-dimensional temperature data of the skin surface. The zoned logic control circuit stores the mapping relationship between sensor coordinates and power transmission plate positions, and independently adjusts the current on / off of the corresponding area's power transmission plate based on coordinate feedback. This enables pinpoint identification and targeted power-off cooling of high-temperature inflamed areas, maintaining heat therapy care for normally healing areas. It solves the problem of uniform temperature control in traditional devices leading to aggravation of local inflammation, and improves the targeted and safe nature of scar prevention.

[0017] 3. This invention introduces a pulsed zero-energy-consumption endurance management strategy system based on PCM latent heat state observation. A phase change energy storage encapsulation unit is filled in the gap of the temperature regulation component. The differential temperature monitoring component collects the temperature difference data between the core and the interface. The logic judgment circuit identifies the heat absorption plateau period of the solid-liquid phase change composite material based on the temperature difference value and the rate of change and cuts off the active cooling power supply. The latent heat is used to maintain a constant temperature environment. The energy consumption is reduced by the pulsed intermittent operation mode, which extends the portable use endurance of the device. A compression deformation layer is set on the inner wall of the phase change energy storage encapsulation unit. When under pressure, it generates backward elastic displacement to provide volume expansion space and ensure the integrity of the encapsulation structure. Attached Figure Description

[0018] Figure 1 This is a perspective view of the entire front of the present invention;

[0019] Figure 2 This is a schematic diagram of a portion of the internal structure of the soft shell of the present invention;

[0020] Figure 3 This is a schematic diagram of half of the internal structure of the soft shell of the present invention;

[0021] Figure 4 This is a schematic diagram of the internal structure of the medical silicone layer of the present invention;

[0022] Figure 5 This is an overall structural diagram of the temperature regulation component of the present invention;

[0023] Figure 6 This is a structural diagram of the heating section in the temperature regulation assembly of the present invention;

[0024] Figure 7This is a structural diagram of the internal filtration section of the air-cooled filter assembly of the present invention;

[0025] Figure 8 This is a structural diagram of the internal air-cooling section of the filter air-cooling assembly of the present invention;

[0026] Figure 9 This is a flowchart of the logic control of the wound inflammation early warning and zoned targeted temperature control system based on thermal imaging matrix of the present invention.

[0027] Figure 10 This is a timing diagram of the pulsed zero-energy-consumption range management strategy based on PCM latent heat state observation of the present invention.

[0028] The components include: 1. Display controller; 1a. LCD screen; 1b. Microprocessor; 1c. Operation button group; 2. Soft shell; 3. Medical silicone layer; 4. Multi-media integrated coupling interface module; 4a. Fixed socket assembly; 4b. Movable plug assembly; 4c. Electrical connection interface; 4d. Fluid connection interface; 4e. Pneumatic connection interface; 5. Power transmission board; 6. Lint hook; 7. Lint trap; 8. Connecting wire; 9. Scale temperature conduction array; 10. Water circulation pipe; 11. Heating wire; 12. Air pump; 13. Temperature guide plate; 14. Nano silver antibacterial layer; 15. Temperature conduction plate; 16. Airbag; 17. Temperature probe; 18. Connecting shell; 19. Protective soft plate; 20. Water tank; 21. Filter plate; 22. Dustproof inclined plate; 23. Fan exterior. 24. Shell; 25. Fan; 26. Filter plate; 27. Support; 28. Dustproof plate; 39. Water pump; 30. Wound inflammation early warning and zoned targeted temperature control system based on thermal imaging matrix; 31. Flexible temperature measurement array layer; 32. Miniature temperature sensor; 33. Copper foil conductive trace; 34. Zoned logic control circuit; 34a. Analog signal acquisition module; 34b. Central processing module; 34c. Power drive module; 35. Pulse-type zero-energy-consumption endurance management strategy system based on PCM latent heat state observation; 40. Phase change energy storage packaging unit; 40a. Packaging shell; 41. Solid-liquid phase change composite material; 42. Elastic buffer structure; 43. Differential temperature monitoring component; 43a. Core temperature probe; 43b. Interface temperature probe; 44. Logic judgment circuit. Detailed Implementation

[0029] The technical solutions in 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.

[0030] Please see the appendix Figure 1 - Appendix Figure 7This invention provides a skin surgical scar prevention and care device based on intelligent temperature control, including a soft shell 2, a temperature conduction plate 15 fixedly connected to the inner bottom of the soft shell 2, and connecting shells 18 fixedly connected to the outer sides of both ends of the soft shell 2. A filter air-cooling component is provided on the inner side of both connecting shells 18, and a temperature adjustment component is provided between the soft shell 2 and the temperature conduction plate 15.

[0031] The temperature conduction plate 15 is equipped with a wound inflammation early warning and zoned targeted temperature control system based on thermal imaging matrix, which is used to collect array temperature data of the skin contact surface and output independent temperature control commands for different areas; the temperature regulation component is equipped with a pulse-type zero-energy-consumption endurance management strategy system based on PCM latent heat state observation, which is used to monitor the phase change plateau state of the internal phase change material and control the start and stop power supply of the temperature regulation component.

[0032] The temperature regulating assembly includes multiple power supply plates 5, all of which are fixedly connected to the top inner side of the flexible shell 2. Multiple heating wires 11 are disposed inside the flexible shell 2, and the power supply plates 5 are respectively fixedly connected to the input ends of the heating wires 11. Protective flexible plates 19 are fixedly connected to both sides of the flexible shell 2, and temperature guide plates 13 are fixedly connected between two protective flexible plates 19. The temperature guide plates 13 are all disposed on the outer side of the multiple heating wires 11. The temperature regulating assembly also includes a water tank 20, which is fixedly connected to the inner side of the flexible shell 2. A water pump 28 is fixedly connected to the inner side of the water tank 20, and the output ends of the water pump 28 are fixedly connected to water circulation pipes 10. The other end of the water circulation pipes 10 is fixedly connected to the inner side of the water tank 20, and the water circulation pipes 10 are also fixedly connected to the inner side of the multiple temperature guide plates 13.

[0033] Specifically, the soft shell 2 is used to carry the internal electrical and mechanical components and conforms to the contours of the human body; the temperature conduction plate 15 is used to establish a heat exchange interface between the device and the skin surface to achieve bidirectional heat transfer; the connecting shell 18 is used to fix and support the air-cooling mechanism; the filter air-cooling component is used to introduce airflow to reduce the internal ambient temperature of the device; the wound inflammation early warning and zoned targeted temperature control system based on thermal imaging matrix acquires temperature field data through matrix sensors to determine and locate inflammation risk points; the pulsed zero-energy endurance management strategy system based on PCM latent heat state observation monitors the physical state of phase change materials and controls the temperature within the phase change range. Active power supply is suspended, and latent heat is used to maintain a constant temperature; the power distribution board 5 is used to distribute electrical energy to the heating zone; the heating wire 11 is used to perform resistance heating function, generating heat energy to apply heat to the low-temperature area; the protective soft plate 19 is used to protect the internal precision components when the soft shell 2 is deformed by pressure; the temperature guide plate 13 is used to build an efficient heat conduction path between the heating wire 11, the water circulation pipe 10 and the temperature conduction plate 15; the water tank 20 is used to store the circulating cooling medium; the water pump 28 is used to provide fluid circulation power; the water circulation pipe 10 is used to guide the flow of the cooling medium and remove the accumulated heat to realize the active cooling function.

[0034] Please see the appendix Figure 7 and attached Figure 8 The air-cooled filter assembly includes a connecting shell 18, which is fixedly connected to the inside of the flexible shell 2. Multiple dustproof inclined plates 22 are fixedly connected to the inner side of the end of the connecting shell 18. Two filter plates 21 are fixedly connected to the inner side of the connecting shell 18. Multiple connecting channels are provided at one end of the flexible shell 2 near the connecting shell 18. A fan housing 23 is fixedly connected to the inner side of the end of the flexible shell 2 and is fixedly connected to the connecting channels. The air-cooled filter assembly also includes multiple brackets 26, which are fixedly connected to the inside of the fan housing 23. A dustproof plate 27 is fixedly connected to one end of the fan housing 23, and multiple filter plates 25 are fixedly connected to the inner side of the other end of the fan housing 23. Fans 24 are installed inside each of the multiple brackets 26.

[0035] Specifically, the connecting shell 18 is used to support external components and establish an air inlet port; the dustproof inclined plate 22 is used to block larger external particles from entering by using a physical tilt angle; the filter plate 21 is used to perform primary screening and filtration of the airflow passing through the connecting shell 18; the connecting channel is used to guide the flow path of external air into the soft shell 2; the fan housing 23 is used to encapsulate the power air supply unit and regulate the flow field direction; the bracket 26 is used to stably support the fan 24 to prevent vibration and displacement; the dustproof plate 27 is used to cooperate with the fan housing 23 to provide secondary protection at the air inlet; the filter plate 25 is used to perform fine dust interception before the airflow comes into contact with the core components; the fan 24 is used to generate negative pressure suction through high-speed rotation to drive the air to form a heat exchange circulation flow inside and outside the device.

[0036] Please see the appendix Figure 4 and attached Figure 5 An airbag 16 is fixedly connected to the bottom outer side of the temperature conduction plate 15. Two air pumps 12 inside both ends of the soft shell 2 are also fixedly connected to the connection channel. The output ends of multiple air pumps 12 are fixedly connected between the temperature conduction plate 15 and the airbag 16. A nano-silver antibacterial layer 14 is fixedly connected to the outside of the airbag 16. A medical silicone layer 3 is fixedly connected to the outside of the nano-silver antibacterial layer 14. Both the medical silicone layer 3 and the nano-silver antibacterial layer 14 are fixedly connected to the outside of the temperature conduction plate 15. Multiple scale temperature conduction arrays 9 are arranged between the medical silicone layer 3 and the nano-silver antibacterial layer 14. Temperature probes 17 are fixedly arranged between the multiple scale temperature conduction arrays 9. Multiple temperature probes 17 are also arranged between the medical silicone layer 3 and the nano-silver antibacterial layer 14. A multi-media integrated coupling interface module 4 is fixedly connected to the outer side of the middle part of the soft shell 2. A connecting line 8 is fixedly connected to the connecting end of the multi-media integrated coupling interface module 4. A display controller 1 is fixedly connected to the connecting end of the connecting line 8. A lint hook 6 is fixedly connected to the outer side of one end of the soft shell 2. A lint adhesive tape 7 is fixedly connected to the outer side of the other end of the soft shell 2. The lint hook 6 is pasted on the outer side of the lint adhesive tape 7.

[0037] Specifically, the airbag 16 is used to inflate and generate flexible pressure, driving the functional layer to fit tightly against the surface of human skin; the air pump 12 is used to provide the pneumatic pressure required for inflation of the airbag 16; the nano-silver antibacterial layer 14 is used to release silver ions to inhibit bacterial growth and maintain a sterile environment for the wound; the medical silicone layer 3 is used as a biocompatible contact interface to reduce discomfort from long-term wear; the scale temperature conduction array 9 is used to maintain high-efficiency heat transfer efficiency while conforming to the bending and deformation of the limb using a biomimetic scale structure; the temperature probe 17 is used to collect high-precision skin temperature signals deep into the contact surface; the multi-media integrated coupling interface module 4 is used to centrally manage circuit signals, fluid and gas pipeline connection interfaces; the display controller 1 is used to visually present monitoring data and provide a human-machine interactive interface; the connecting line 8 is used to transmit control signals and electrical energy; the hook strap 6, together with the sticky strap 7, is used to securely wear the device on the patient's treatment site through mechanical interlocking.

[0038] The present invention provides a skin surgical scar prevention and care device based on intelligent temperature control, which further includes: a wound inflammation early warning and zoned targeted temperature control system 30 based on thermal imaging matrix and a pulsed zero-energy endurance management strategy system 35 based on PCM latent heat state observation.

[0039] The wound inflammation early warning and zoned targeted temperature control system 30 based on thermal imaging matrix is ​​disposed within the internal structure of the temperature conduction plate 15. This system includes a flexible temperature sensing array layer 31, which is physically embedded within the interlayer space of the temperature conduction plate 15. Specifically, the temperature conduction plate 15 adopts a sandwich composite structure, consisting of an upper thermally conductive silicone sheet, a middle flexible temperature sensing array layer 31, and a lower high thermal conductivity insulating film laminated together.

[0040] The flexible temperature measurement array layer 31 is located in the middle layer in its thickness direction. This "embedded" design not only protects the sensor from external mechanical wear, but also prevents local pressure damage through the buffering effect of the upper and lower layers.

[0041] The main substrate of the flexible temperature sensing array layer 31 adopts a flexible printed circuit board (FPC) structure, and the insulating bottom layer material is a high-heat-resistant polyimide (PI) film with a thickness set between 0.05 mm and 0.15 mm. This thickness range has been optimized to give the substrate mechanical flexibility with a minimum bending radius of 5 mm, thereby enabling it to closely conform to the irregular curved contours of the human body, while providing electrical insulation performance with a breakdown voltage greater than 3 kV.

[0042] The flexible temperature sensing array layer 31 includes multiple miniature temperature sensors 32 arranged according to a preset row and column rule. These sensors are fixedly soldered to the surface of the main substrate and arranged according to a Cartesian coordinate system matrix rule. The multiple miniature temperature sensors 32 are arranged along the longitudinal and transverse directions of the temperature conduction plate 15. Each miniature temperature sensor 32 corresponds to a unique physical coordinate position, and this matrix distribution covers the effective working area of ​​the temperature conduction plate 15 in contact with the skin. The miniature temperature sensors 32 are configured to sense and output real-time temperature signals of the contact surface of the temperature conduction plate 15. The miniature temperature sensors 32 are surface-mount negative temperature coefficient (NTC) thermistors with package sizes of 0201 or 0402 imperial units to achieve millisecond-level response to heat changes by utilizing their low thermal capacity. To improve measurement accuracy, the B-value tolerance of the NTC thermistor is controlled within ±1%, and a "U"-shaped trace layout is used on the substrate to reduce the impact of stress on the solder joints.

[0043] Copper foil conductive traces 33 are formed on the flexible temperature sensing array layer 31 through an etching process, connecting the two electrodes of each miniature temperature sensor 32 and converging to the edge connector. The copper foil conductive traces 33 are covered with a flexible solder mask insulating layer. In order to achieve high-density wiring in a limited space, the copper foil conductive traces 33 adopt a multi-layer buried via process and are provided with a grid-like ground shielding layer to prevent external electromagnetic interference from affecting the weak analog temperature signal.

[0044] The flexible temperature sensing array layer 31 is fixed to the temperature conduction plate 15 by a thermally conductive insulating adhesive layer with a thermal conductivity greater than 1.5 watts per meter Kelvin (W / (m·K)), ensuring vertical heat conduction and blocking leakage current.

[0045] The conversion relationship between the resistance value and temperature of the miniature temperature sensor 32 follows the beta parameter equation. In this embodiment, the reciprocal of the Kelvin temperature value at the coordinate is equal to the reciprocal of the reference temperature value plus the natural logarithm of the ratio of the real-time resistance measurement value to the nominal resistance value, divided by the thermistor constant.

[0046] The wound inflammation early warning and zoned targeted temperature control system 30 based on thermal imaging matrix includes a zoned logic control circuit 34. This circuit is physically integrated on the PCB motherboard inside the multi-media integrated coupling interface module 4, or it is located inside the display controller 1 and interacts with data via the connecting line 8. The zoned logic control circuit 34 is divided into an analog signal acquisition module 34a, a central processing module 34b, and a power drive module 34c.

[0047] The analog signal acquisition module 34a is connected one-to-one with multiple miniature temperature sensors 32 via copper foil conductive traces 33. This direct connection method ensures the independence and real-time nature of the data from each sensor, avoiding scanning delay. In the measurement loop, each miniature temperature sensor 32 is connected in series with a precision reference resistor between the reference voltage source and ground (GND). The analog signal acquisition module 34a transmits the analog voltage signals from both ends of the sensor to a 12-bit or higher resolution analog-to-digital converter. To eliminate errors caused by wire resistance, a Kelvin four-wire detection mechanism or software compensation algorithm is also integrated into the circuit. The correspondence between the voltage signal and the real-time resistance value follows the calculation principle of a voltage divider circuit, that is, the sampled voltage value is equal to the reference voltage multiplied by the ratio of the resistance to be measured to the sum of the reference resistance and the resistance to be measured.

[0048] The central processing module 34b employs a microcontroller (MCU), specifically a low-power chip with an ARM Cortex-M4 or higher core and a clock frequency of at least 80MHz to meet the requirements of matrix floating-point operations. The partitioned logic control circuit 34 is configured to store the mapping relationship between sensor coordinates and power supply board positions; that is, a table showing the correspondence between the heating wire 11 being divided into K independent heating temperature zones and the sensor coordinates. The power drive module 34c is mounted on multiple power supply boards 5, corresponding to the number of temperature zones, and includes MOSFET power switching transistor assemblies. Each MOSFET power switching transistor assembly is equipped with an optocoupler to achieve electrical isolation between the control signals and the power circuit, preventing power fluctuations from interfering with the logic circuit.

[0049] The central processing module 34b independently controls the on / off state of each power supply board 5 through GPIO pins.

[0050] The central processing module 34b runs an inflammation detection algorithm. Based on whether the temperature signal fed back by the miniature temperature sensor exceeds a preset threshold, it generates a targeted control signal to switch the current on / off state of the corresponding area's power supply board 5. Specifically, the detection logic is as follows: when the temperature value at a certain coordinate is greater than the sum of the preset standard nursing temperature and the inflammation temperature difference threshold, it is determined to be an inflammation risk state, i.e., the inflammation warning flag is set to 1; otherwise, it is determined to be a normal state, and the flag is set to 0. To prevent false alarms in critical states, a time integration mechanism is introduced into the algorithm, meaning that the warning flag is only set after the temperature has continuously exceeded the threshold for a set time (e.g., 5 seconds).

[0051] When the inflammation detection algorithm, running through the central processing module 34b, determines that there is a risk of inflammation at any location, the system triggers zone-targeted cooling, cutting off the power supply to the corresponding temperature zone's power supply board 5 and activating global cooling (driving the water pump 28 and fan 24). When there is no inflammation warning in all areas and the temperature in some areas is lower than the preset standard care temperature, the system performs zone-targeted heating. The central processing module 34b generates a duty cycle control signal based on the proportional and integral terms of the temperature difference, driving the corresponding power supply board 5 and heating wire 11 for proportional heating.

[0052] The device also includes a pulsed zero-energy endurance management strategy system 35 based on PCM latent heat state observation, the core of which is a phase change energy storage encapsulation unit 40 filled in the internal cavity of the soft shell 2. This unit is located at the gap between the heating wire 11 and the temperature conductor 13, and is in close thermal contact with the temperature conductor 13. The phase change energy storage encapsulation unit 40 includes an encapsulation shell 40a made of a double-layer aluminum-plastic composite film by hot pressing. This aluminum-plastic film has a three-layer structure of nylon layer, aluminum foil layer and heat-sealing layer, which has strong barrier properties and can effectively prevent the leakage of phase change material. The interior is filled with solid-liquid phase change composite material 41.

[0053] Solid-liquid phase change composite material 41 is determined by the phase change melting point temperature A binary eutectic mixture of n-octadecane and n-eicosane at 28 to 30 degrees Celsius was used as the matrix, and 5% to 8% by mass of expanded graphite powder was added as a thermally conductive reinforcing filler to increase the thermal conductivity to over 1.0 W / (m·K). During the preparation process, ultrasonic dispersion technology was used to ensure that the expanded graphite was uniformly distributed in the matrix, forming a thermally conductive percolation network, thus avoiding sedimentation and stratification after long-term use.

[0054] The inner wall of the encapsulation housing 40a is bonded with an elastic buffer structure 42 made of micro-foamed TPU material. The elastic buffer structure 42 is a compression deformation layer that fits the inner wall of the phase change energy storage encapsulation unit 40. The compression deformation layer is configured to generate a backward elastic displacement when subjected to internal pressure to provide space for the volume expansion of the solid-liquid phase change composite material.

[0055] The minimum reserved volume of the elastic buffer structure 42 is designed and calculated based on the mass of the phase change material, the density difference between the liquid and solid states, and the safety factor.

[0056] The pulsed zero-energy endurance management strategy system 35 based on PCM latent heat state observation includes a differential temperature monitoring component 43, consisting of a core temperature probe 43a (one implementation of temperature probe 17) and an interface temperature probe 43b. The core temperature probe 43a is embedded in the geometric center of the solid-liquid phase change composite material 41, and the interface temperature probe 43b is fixed to the contact interface between the encapsulation housing 40a and the temperature guide plate 13. Both are connected to a logic judgment circuit 44, which is configured to calculate the real-time temperature difference between the core temperature probe and the interface temperature probe, and determine whether the solid-liquid phase change composite material is in the isothermal endothermic stage based on the temperature difference value and the rate of change. The logic judgment circuit 44 integrates a hysteresis comparator, which, by setting upper and lower threshold values, avoids frequent switching between active and passive modes due to signal fluctuations at the phase change critical point.

[0057] The logic judgment circuit 44 executes a zero-energy control strategy based on the monitoring data. Its power-on duty cycle follows the energy balance principle, that is, the product of the active cooling power and the control cycle should balance the difference between the heat load and the latent heat value.

[0058] The multi-media integrated coupling interface module 4 is located on the side edge of the soft shell 2, integrating a fixed socket assembly 4a and a movable plug assembly 4b connected to the connecting line 8. Internally, it is divided into a dry area containing an electrical connection interface 4c and a wet area containing a fluid connection interface 4d and a pneumatic connection interface 4e. The electrical connection interface 4c connects to the power supply board 5, the flexible temperature sensing array layer 31, and the differential temperature monitoring assembly 43 via conductive pins. The fluid connection interface 4d connects to the water circulation pipe 10 and has a built-in self-sealing check valve. The pneumatic connection interface 4e connects to the airbag 16.

[0059] The display controller 1 is connected to the multi-media integrated coupling interface module 4 via a connecting cable 8. It includes an LCD screen 1a, a microprocessor 1b, and a set of operation buttons 1c. The microprocessor 1b renders the received two-dimensional temperature matrix data into a pseudo-color thermal image for display and triggers an audible and visual alarm based on the warning status.

[0060] The workflow of this invention includes the wearing and fitting stage:

[0061] The operator covers the wound with the soft shell 2 and secures it using the annular strap 7 and hook strap 6. Pressing the inflation button activates the air pump 12, which inflates the airbag 16 via the multi-media integrated coupling interface module 4. The inflated airbag 16 pushes the rigid support plate 29, causing the temperature conduction plate 15 and the medical silicone layer 3 to adhere to the skin. The thrust generated by the airbag 16 is determined by the product of the preset air pressure and the contact area. After adhesion, the system verifies the validity of the temperature reading.

[0062] Please see the appendix Figure 9 , attached Figure 9This is a flowchart of the logic control of the wound inflammation early warning and zoned targeted temperature control system based on thermal imaging matrix of the present invention.

[0063] This diagram illustrates the complete closed-loop logic from temperature matrix scanning and inflammation risk assessment to the execution of zoned cooling or heating control. It clearly reflects the process by which the microcontroller makes judgments based on the aforementioned judgment logic and branches out to execute different thermal management strategies.

[0064] Workflow of intelligent monitoring and temperature control stage:

[0065] Step 1: Periodic scanning of the temperature matrix. The central processing module 34b drives the analog signal acquisition module 34a at a fixed frequency (1 Hz to 10 Hz), sequentially selects and measures the voltage signal of each miniature temperature sensor 32 through a one-to-one connection channel, and calculates the two-dimensional temperature matrix according to the aforementioned calculation logic.

[0066] Step Two: Real-time Inflammation Risk Assessment. The central processing module 34b performs calculations on the matrix elements according to the aforementioned assessment logic. If any coordinate point meets the inflammation risk condition, an inflammation risk is determined to exist, and the process proceeds to Step Three; otherwise, the process proceeds to Step Four.

[0067] Step 3: Targeted cooling of high-temperature areas. The system determines the heating zone number k corresponding to the high-temperature coordinates, sends a shutdown command to the corresponding power supply board 5 to cut off the power supply to the heating wire 11 in that area, sends an alarm frame to the display controller 1, and outputs a global cooling signal to drive the water pump 28 and fan 24 to run at full power.

[0068] Step 4: Dynamic heating of low-temperature areas. When there is no inflammation warning in all areas and low-temperature areas exist, the system calculates the average temperature of each temperature zone, generates a PWM signal based on the aforementioned proportional-integral control logic, and drives the corresponding power supply board 5 and heating wire 11 to perform proportional heating.

[0069] Step 5: PCM Latent Heat Status Collaborative Management. The logic judgment circuit 44 synchronously collects data from the core temperature probe 43a and the interface temperature probe 43b. When it is determined that the phase transition plateau period has been entered (i.e., the difference between the core temperature and the melting point is extremely small and the core temperature change rate approaches zero) and cooling is required, the power supply to the active cooling equipment is cut off, and the system enters a zero-energy maintenance mode. When latent heat is detected to be depleted, active energy replenishment is restarted.

[0070] Step Six: Human-Machine Interaction Status Update. Display controller 1 renders thermal images in real time, marks high-temperature areas, displays the operating mode, and stores the data.

[0071] Please see the appendix Figure 10 , attached Figure 10 This is a timing diagram of the pulsed zero-energy-consumption range management strategy based on PCM latent heat state observation of the present invention.

[0072] The graph, with time as the horizontal axis, shows the relationship between core temperature, interface temperature, and the power of the active cooling system over time. It clearly marks the switching points between the active cooling phase, the zero-energy latent heat maintenance phase (phase change plateau), and the active recharging phase after latent heat depletion, intuitively demonstrating the pulsed operating principle based on energy balance.

[0073] Zero-energy range control timing:

[0074] Step 1: Zero-energy entry condition determination. Triggered when the following conditions are met simultaneously:

[0075] The absolute value of the difference between the core temperature and the melting point is less than 0.5 degrees Celsius;

[0076] The absolute value of the core temperature change rate is less than 0.01 degrees Celsius per second;

[0077] The interface temperature is higher than the core temperature;

[0078] The system is in a state of cooling demand.

[0079] Step 2: Shut down the active cooling equipment. The system sends a command to shut down water pump 28 and fan 24, stopping the active circulation.

[0080] Step 3: Phase change latent heat maintenance stage. The solid-liquid phase change composite material 41 absorbs heat from the temperature conductor 13 by melting. The absorbed energy is equal to the mass of the phase change material multiplied by the latent heat value, thus maintaining the temperature conduction plate 15 near the melting point temperature.

[0081] Step 4: Latent heat depletion monitoring. Continuously monitor the core temperature and temperature difference. When the core temperature is significantly higher than the melting point, or the temperature difference is too small, or the rate of temperature change is too large, latent heat depletion is determined.

[0082] Step 5: Active energy replenishment phase begins. Restart water pump 28 (flow rate ≥ 100 ml / min) and fan 24 (wind speed ≥ 1.5 m / s) to actively cool and recrystallize the phase change material.

[0083] Step Six: Solidification Process Monitoring. When the core temperature drops below the set value below the melting point and the rate of change stabilizes, solidification is deemed complete, the active equipment is shut down, and the monitoring cycle returns. This pulsed operation achieves low duty cycle or zero power consumption operation based on the aforementioned energy balance principle.

Claims

1. A skin surgical scar prevention and care device based on intelligent temperature control, characterized in that, include: A soft shell (2) is fixedly connected to a temperature conduction plate (15) on the inner side of the bottom of the soft shell (2). A connecting shell (18) is fixedly connected to the outer sides of both ends of the soft shell (2). A filter air-cooling component is provided on the inner side of both connecting shells (18). A temperature regulating component is provided between the soft shell (2) and the temperature conduction plate (15). The temperature conduction plate (15) is equipped with a wound inflammation early warning and zoned targeted temperature control system based on thermal imaging matrix, which is used to collect array temperature data of the skin contact surface and output independent temperature control commands for different areas; the temperature regulation component is equipped with a pulse-type zero-energy-consumption endurance management strategy system based on PCM latent heat state observation, which is used to monitor the phase change plateau state of the internal phase change material and control the start and stop power supply of the temperature regulation component. The temperature regulating component includes multiple power transmission plates (5), which are fixedly connected to the top inner side of the soft shell (2). Multiple heating wires (11) are provided inside the soft shell (2). The multiple power transmission plates (5) are fixedly connected to the input end of the heating wires (11). Protective soft plates (19) are fixedly connected to both sides of the soft shell (2). Temperature guide plates (13) are fixedly connected between two protective soft plates (19). The multiple temperature guide plates (13) are all arranged on the outside of the multiple heating wires (11).

2. The skin surgical scar prevention and care device based on intelligent temperature control according to claim 1, characterized in that, The temperature regulating component also includes a water tank (20), which is fixedly connected to the inside of the soft shell (2). A water pump (28) is fixedly connected to the inside of the water tank (20). The output end of the water pump (28) is fixedly connected to a water circulation pipe (10). The other end of the water circulation pipe (10) is fixedly connected to the inside of the water tank (20). The water circulation pipe (10) is also fixedly connected to the inside of a plurality of temperature guide plates (13).

3. The skin surgical scar prevention and care device based on intelligent temperature control according to claim 1, characterized in that, The air-cooled filter assembly includes a connecting shell (18), which is fixedly connected to the inner side of the soft shell (2). Multiple dustproof inclined plates (22) are fixedly connected to the inner side of the end of the connecting shell (18). Two filter screens (21) are fixedly connected to the inner side of the connecting shell (18). Multiple connection channels are provided at one end of the soft shell (2) near the connecting shell (18). A fan housing (23) is fixedly connected to the inner side of the end of the soft shell (2). The fan housing (23) is fixedly connected in the connection channels.

4. A skin surgical scar prevention and care device based on intelligent temperature control according to claim 3, characterized in that, The air-cooled filter assembly also includes multiple brackets (26), which are fixedly connected inside the fan housing (23). A dustproof plate (27) is fixedly connected to one end of the fan housing (23), and multiple filter plates (25) are fixedly connected to the inner side of the other end of the fan housing (23). A fan (24) is installed inside each of the multiple brackets (26).

5. A skin surgical scar prevention and care device based on intelligent temperature control according to claim 1, characterized in that, An airbag (16) is fixedly connected to the bottom outer side of the temperature conduction plate (15). Two air pumps (12) inside both ends of the soft shell (2) are also fixedly connected to the connection channel. The output ends of multiple air pumps (12) are fixedly connected between the temperature conduction plate (15) and the airbag (16). A nano-silver antibacterial layer (14) is fixedly connected to the outside of the airbag (16). A medical silicone layer (3) is fixedly connected to the outside of the nano-silver antibacterial layer (14). Both the medical silicone layer (3) and the nano-silver antibacterial layer (14) are fixedly connected to the outside of the temperature conduction plate (15). Multiple scale temperature conduction arrays (9) are provided between the medical silicone layer (3) and the nano-silver antibacterial layer (14). Temperature probes (17) are fixedly provided between the multiple scale temperature conduction arrays (9). Multiple temperature probes (17) are also provided between the medical silicone layer (3) and the nano-silver antibacterial layer (14).

6. A skin surgical scar prevention and care device based on intelligent temperature control according to claim 1, characterized in that, The soft shell (2) is fixedly connected to a multi-media integrated coupling interface module (4) on the outer side of the middle part. The connection end of the multi-media integrated coupling interface module (4) is fixedly connected to a connecting line (8). The connection end of the connecting line (8) is fixedly connected to a display controller (1). The outer side of one end of the soft shell (2) is fixedly connected to a lint hook (6). The outer side of the other end of the soft shell (2) is fixedly connected to a lint adhesive tape (7). The lint hook (6) is pasted on the outer side of the lint adhesive tape (7).

7. A skin surgical scar prevention and care device based on intelligent temperature control according to claim 1, characterized in that, The wound inflammation early warning and zoned targeted temperature control system based on thermal imaging matrix includes a flexible temperature measurement array layer, which is embedded in the internal interlayer of the temperature conduction plate (15). The flexible temperature measurement array layer contains multiple micro temperature sensors arranged according to a preset row and column rule. The multiple micro temperature sensors are configured to sense and output the real-time temperature signal of the contact surface of the temperature conduction plate (15).

8. A skin surgical scar prevention and care device based on intelligent temperature control according to claim 7, characterized in that, The wound inflammation early warning and zoned targeted temperature control system based on thermal imaging matrix also includes a zoned logic control circuit. The signal input terminal of the zoned logic control circuit is connected to multiple miniature temperature sensors. The control output terminal of the zoned logic control circuit is electrically connected to multiple power transmission boards (5). The zoned logic control circuit is configured to store the mapping relationship between sensor coordinates and power transmission board positions, and generate targeted control signals to switch the current on / off state of the power transmission board (5) in the corresponding area based on whether the temperature signal fed back by the miniature temperature sensor exceeds a preset threshold.

9. A skin surgical scar prevention and care device based on intelligent temperature control according to claim 1, characterized in that, The pulsed zero-energy-consumption range management strategy system based on PCM latent heat state observation includes a phase change energy storage encapsulation unit. The phase change energy storage encapsulation unit is filled inside the soft shell (2) and located in the gap of the temperature regulation component. The phase change energy storage encapsulation unit is filled with a solid-liquid phase change composite material. The inner wall of the phase change energy storage encapsulation unit is provided with an elastic buffer structure. The elastic buffer structure is a compression deformation layer that fits the inner wall. The compression deformation layer is configured to generate a backward elastic displacement when subjected to internal pressure to provide space for the volume expansion of the solid-liquid phase change composite material.

10. A skin surgical scar prevention and care device based on intelligent temperature control according to claim 9, characterized in that, The pulsed zero-energy endurance management strategy system based on PCM latent heat state observation also includes a differential temperature monitoring component. The differential temperature monitoring component includes a core temperature probe and an interface temperature probe. The core temperature probe is fixedly set at the geometric center of the solid-liquid phase change composite material, and the interface temperature probe is fixedly set at the outer boundary of the phase change energy storage encapsulation unit. Both the core temperature probe and the interface temperature probe are connected to a logic judgment circuit. The logic judgment circuit is configured to calculate the real-time temperature difference between the core temperature probe and the interface temperature probe, and determine whether the solid-liquid phase change composite material is in the isothermal heat absorption stage based on the real-time temperature difference value and the rate of change.

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