Inhalation type cold air therapy instrument and temperature control method

Abstract

The application relates to an inhaled cold air treatment instrument and a temperature control method, and belongs to the medical instrument field. The application comprises a case, a flow regulating valve, an air inlet pipe, a heat exchange unit, a temperature sensor, a control unit, a heat preservation pipeline, a patient interface, a display control panel and a gas bottle. The heat exchange unit and the control unit are arranged in the case. The front panel of the case is provided with the display control panel. The heat exchange unit is provided with an air inlet and an air outlet. One end of the air inlet pipe is connected with the gas bottle, and the other end is connected with the air inlet through the flow regulating valve. The patient interface is connected with the air outlet through the heat preservation pipeline. The temperature sensor is arranged on the heat preservation pipeline. The control unit is connected with the flow regulating valve, the heat exchange unit, the temperature sensor and the display control panel. The application solves the problems of slow effect, large side effect and poor patient compliance of the existing systemic or invasive hypothermia treatment method, and lacks an effective means for targeted hypothermia protection of the heart region through the respiratory tract.

Description

Technical Field

[0001] This invention relates to an inhalation-type cold air therapy device and a temperature control method, belonging to the field of medical devices. Background Technology

[0002] Myocardial infarction is one of the leading causes of disability and death worldwide. Currently, clinical reperfusion therapy (such as thrombolysis and PCI) and standardized drug therapy have significantly improved acute-phase survival rates. However, myocardial infarction patients still face a high risk of poor long-term outcomes. Some patients develop serious complications such as heart failure, arrhythmias, and re-infarction, leading to decreased cardiac function, deteriorated quality of life, and increased risk of death. This remains a significant challenge in the clinical management of cardiovascular diseases.

[0003] In recent years, hypothermia therapy (or hypothermia therapy) has shown great potential in the fields of neuroprotection and myocardial protection. Studies have shown that systemic or localized hypothermia can reduce infarct size, improve cardiac function, and mitigate reperfusion injury. Its protective mechanisms may include reducing metabolic rate, inhibiting inflammatory responses, and reducing oxidative stress and apoptosis.

[0004] However, existing cryotherapy techniques mainly focus on surface cooling (such as ice blankets and ice caps) or invasive intravascular cooling catheters. These methods have the following significant drawbacks:

[0005] 1. Insufficient efficiency and speed: The body surface cooling rate is slow, making it difficult to quickly reach and maintain the target temperature, which may cause the best treatment window to be missed;

[0006] 2. Significant side effects: Systemic hypothermia can easily lead to complications such as shivering, arrhythmia, coagulation dysfunction, and increased risk of infection, making clinical management complex;

[0007] 3. Poor comfort and compliance: Surface cooling methods are uncomfortable for patients and are difficult to use for long-term or preventative treatment;

[0008] 4. Lack of targeting: Current technology lacks targeted temperature management of the respiratory tract, and cannot achieve targeted hypothermia protection of the heart area through the respiratory route.

[0009] Therefore, there is an urgent need to develop an inhaled cold air therapy device and temperature control method that can quickly, accurately, and non-invasively apply the hypothermic protective effect to the heart area, with minimal side effects and high patient compliance, in order to solve the aforementioned technical problems. Summary of the Invention

[0010] The purpose of this invention is to address the problems of slow onset of action, significant side effects, and poor patient compliance in existing systemic or invasive hypothermia treatments, as well as the lack of effective means for targeted hypothermia protection of the cardiac region via the respiratory tract. A brief overview of this invention is provided below to offer a basic understanding of certain aspects of the invention. It should be understood that this overview is not an exhaustive summary of the invention. It is not intended to identify key or essential parts of the invention, nor is it intended to limit the scope of the invention.

[0011] The technical solution of the present invention:

[0012] An inhalation-type cold air therapy device includes a chassis, a flow regulating valve, an air inlet pipe, a heat exchange unit, a temperature sensor, a control unit, an insulated pipeline, a patient interface, a display control panel, and a gas cylinder. The heat exchange unit and the control unit are installed inside the chassis. The display control panel is installed on the front panel of the chassis. The heat exchange unit has an air inlet and an air outlet. One end of the air inlet pipe is connected to the gas cylinder, and the other end is connected to the air inlet through the flow regulating valve. The patient interface is connected to the air outlet through the insulated pipeline, and a temperature sensor is installed on the insulated pipeline. The control unit is connected to the flow regulating valve, the heat exchange unit, the temperature sensor, and the display control panel.

[0013] Preferably, the heat exchange unit includes an aluminum alloy flow channel block, a temperature-conducting coil, and a semiconductor cooling chip. The aluminum alloy flow channel block has a serpentine slot for accommodating the temperature-conducting coil. The temperature-conducting coil is embedded in the serpentine slot and is in close contact with the aluminum alloy flow channel block to achieve heat conduction. The cold end face of the semiconductor cooling chip is attached to the surface of the aluminum alloy flow channel block with high thermal conductivity silicone grease for cooling the gas flowing through the temperature-conducting coil through the aluminum alloy flow channel block. The two ends of the temperature-conducting coil are the air inlet and the air outlet, respectively.

[0014] Preferably, the hot end face of the semiconductor cooling chip is connected to a copper heat dissipation fin assembly, and an exhaust cooling fan is arranged between the copper heat dissipation fin assemblies.

[0015] Preferably, a top plate is installed on the top of the copper heat dissipation fin assembly, which presses the copper heat dissipation fin assembly, the semiconductor cooling chip and the aluminum alloy flow channel block together, so that the cold end face of the semiconductor cooling chip is tightly pressed against the aluminum alloy flow channel block.

[0016] Preferably, the aluminum alloy flow channel block is covered with thermal insulation cotton, and multiple cooling fans are installed on the side wall of the chassis to allow air to circulate inside.

[0017] Preferably, the temperature sensor includes a first temperature sensor and a second temperature sensor. The first temperature sensor is located on the side of the insulated pipe near the air outlet connection, and the second temperature sensor is located on the side of the insulated pipe near the patient interface connection.

[0018] Preferably, the insulated pipeline includes an internal gas passage and an external insulation layer, with the external insulation layer fitted over the internal gas passage.

[0019] Preferably, the first temperature sensor is connected to the internal gas passage through a Y-shaped tee, that is, the straight end of the Y-shaped tee is connected to the internal gas passage, and the first temperature sensor is installed in the beveled branch of the Y-shaped tee, so that the probe of the first temperature sensor is inserted into the position close to the inner wall of the pipe of the internal gas passage.

[0020] Preferably, the first temperature sensor is connected to the internal gas passage through a six-way converter, that is, the two straight ends of the six-way converter are connected to the internal gas passage, one end of the branch of the six-way converter is connected to the patient interface, and at least one end of the other branches is equipped with a second temperature sensor, so that the probe of the second temperature sensor is inserted into the position close to the inner wall of the pipe of the internal gas passage.

[0021] Option 1: A temperature control method for an inhalation-type cold air therapy device, implemented using the aforementioned therapy device, comprising:

[0022] Step 1: The control unit acquires the preset target temperature value and reads the current actual temperature value collected by the temperature sensor in real time;

[0023] Step 2: The control unit calculates the temperature error between the target temperature value and the current actual temperature value;

[0024] Step 3: The control unit uses a PID control algorithm to perform proportional, integral, and derivative operations on the temperature error to generate a control signal for adjusting the cooling power of the semiconductor refrigeration chip.

[0025] Step 4: The control unit adjusts the output power of the thermoelectric cooler according to the control signal;

[0026] Step 5: Repeat steps 1 to 4 until the current actual temperature value converges within the preset accuracy range of the target temperature value.

[0027] The present invention has the following beneficial effects:

[0028] 1. This invention involves inhaling cooling gas through the respiratory tract. After gas exchange in the lungs, the cooled blood can quickly return to the heart, achieving targeted cooling of the heart area. Compared with surface cooling methods, it takes effect faster and is beneficial for seizing the golden treatment window after myocardial infarction.

[0029] 2. This invention avoids the invasive operation risks and related infection risks of intravascular cooling catheters, resulting in higher patient acceptance and compliance;

[0030] 3. This invention only cools the inhaled gas locally, avoiding serious systemic side effects such as shivering and coagulation disorders caused by systemic hypothermia, making clinical management simpler;

[0031] 4. This invention employs a PID closed-loop feedback control algorithm, combined with real-time monitoring by dual temperature sensors, to ensure that the output gas temperature is precisely stabilized within the set target temperature range of ±0.5℃, thus guaranteeing the repeatability and reliability of the treatment. Attached Figure Description

[0032] Figure 1 This is a schematic diagram of the structure of an inhalation-based cold air therapy device;

[0033] Figure 2 This is a structural diagram of the chassis;

[0034] Figure 3 This is a schematic diagram showing the combination of the copper heat sink fin assembly and the exhaust cooling fan;

[0035] Figure 4 This is a diagram showing the connection between the computer case and the cooling fan;

[0036] Figure 5 This is a schematic diagram of the heat exchange unit.

[0037] Figure 6 This is a schematic diagram showing the combination of copper heat sink fins and semiconductor cooling chip;

[0038] Figure 7 This is a schematic diagram showing the fit between the aluminum alloy flow channel block and the temperature conductive coil;

[0039] Figure 8 This is a structural diagram of an insulated pipeline.

[0040] In the diagram: 1-Chassis, 2-Flow regulating valve, 3-Inlet pipe, 4-Heat exchange unit, 6-Control unit, 7-Insulated piping, 8-Patient interface, 9-Display control panel, 10-Gas cylinder, 11-Cooling fan, 41-Inlet, 42-Outlet, 43-Aluminum alloy flow channel block, 44-Temperature conductive coil, 45-Semiconductor cooling chip, 46-Copper heat dissipation fin assembly, 47-Outlet cooling fan, 48-Top plate, 49-Insulation cotton, 51-First temperature sensor, 52-Second temperature sensor, 71-Internal gas passage, 72-External insulation layer, 73-Y-type tee connector, 74-Six-way adapter, 75-Plug. Detailed Implementation

[0041] To make the objectives, technical solutions, and advantages of this invention clearer, the invention is described below with reference to specific embodiments shown in the accompanying drawings. However, it should be understood that these descriptions are merely exemplary and not intended to limit the scope of the invention. Furthermore, descriptions of well-known structures and technologies are omitted in the following description to avoid unnecessarily obscuring the concept of the invention.

[0042] The connections mentioned in this invention are divided into fixed connections and detachable connections. Fixed connections (i.e., non-detachable connections) include, but are not limited to, conventional fixed connection methods such as folded connections, riveted connections, adhesive connections, and welded connections. Detachable connections include, but are not limited to, conventional disassembly methods such as threaded connections, snap-fit ​​connections, pin connections, and hinged connections. When a specific connection method is not explicitly defined, it is assumed that at least one existing connection method can always be found to achieve the function, and those skilled in the art can choose according to their needs. For example, a welded connection can be chosen for fixed connections, and a hinged connection can be chosen for detachable connections.

[0043] Example 1: Combination Figures 1-8 This embodiment describes an inhalation-type cold air therapy device used to provide myocardial infarction patients with precisely controllable low-temperature gas inhalation therapy. It includes a housing 1, a flow regulating valve 2, an air inlet pipe 3, a heat exchange unit 4, a temperature sensor, a control unit 6, an insulated pipeline 7, a patient interface 8, a display control panel 9, and a gas cylinder 10.

[0044] The chassis 1 consists of a base plate, side pillars, side panels and a front panel. The base plate, side panels and front panel are connected by the side pillars to form a hollow box structure. The whole is made of metal and the chassis 1 has handles for easy handling.

[0045] The front panel of the chassis 1 is equipped with a display control panel 9, which is a touch screen display for real-time display of parameters such as set temperature, cold end temperature, mask temperature, oxygen concentration, and working time. At the same time, the target temperature value can be directly set through touch operation, and the oxygen concentration can detect whether oxygen is leaking.

[0046] The chassis 1 houses a switching power supply, a heat exchange unit 4, and a control unit 6. Multiple cooling fans 11, including intake and exhaust fans, are mounted on the side panel of chassis 1 to form an internal cooling airflow, ensuring stable long-term system operation.

[0047] Gas cylinder 10 is a medical oxygen cylinder or compressed air cylinder, connected to the air inlet 41 located on the chassis 1 via a standard quick connector. One end of the air inlet pipe 3 is connected to the air inlet 41, and the other end is connected to the air inlet 41 of the heat exchange unit 4 via the flow regulating valve 2. The flow regulating valve 2 can be a manual knob type, but in this embodiment, it is replaced by an electric proportional valve driven by a stepper motor to realize digital setting and automatic control of the flow rate. The gas flow rate adjustment range is 0 to 10 L / min, and the commonly used clinical value is 5 to 8 L / min.

[0048] The heat exchange unit 4 is used to precisely cool the room temperature gas to the set treatment temperature. The heat exchange unit 4 includes an aluminum alloy flow channel block 43, a temperature-conducting coil 44, and a semiconductor cooling chip 45. The aluminum alloy flow channel block 43 is machined from a single piece of aluminum alloy plate, and its upper surface is grooved to form a serpentine slot. The depth of the serpentine slot was experimentally optimized to 3.2 mm. Compared to a depth of 3 mm, this dimension allows the temperature-conducting coil to be more fully embedded, significantly improving the heat exchange effect. Experiments show that the lowest gas temperature is -3℃ when the slot depth is 3 mm, and can reach -7℃ when the depth is 3.2 mm.

[0049] The temperature-conducting coil 44 is made of stainless steel, with a total length of approximately 1.2 meters and an inner diameter of 3 millimeters. It is bent into a serpentine coil shape and then completely embedded in the serpentine groove of the aluminum alloy flow channel block, achieving efficient heat conduction by tightly fitting the aluminum alloy flow channel block. The two ends of the temperature-conducting coil 44 are the air inlet 41 and the air outlet 42, respectively.

[0050] The aluminum alloy flow channel block 43 is surrounded by insulation cotton 49 to reduce the loss of cold energy to the environment and improve refrigeration efficiency.

[0051] The cold end face of the thermoelectric cooler 45 is attached to the upper surface of the aluminum alloy flow channel block 43 with high thermal conductivity silicone grease, which is used to conduct cold energy to the gas in the temperature-conducting coil 44 through the aluminum alloy flow channel block. The hot end face of the thermoelectric cooler 45 is connected to a copper heat sink fin assembly 46, and an exhaust cooling fan 47 is arranged between the copper heat sink fin fin assemblies. A top plate 48 is installed on the top of the copper heat sink fin assembly 46. The top plate applies downward pressure by screws or other means to press the copper heat sink fin assembly, the thermoelectric cooler, and the aluminum alloy flow channel block into a whole, ensuring that the cold end face of the thermoelectric cooler is tightly pressed against the aluminum alloy flow channel block and eliminating contact thermal resistance.

[0052] The heat-insulating pipe 7 is connected between the air outlet 42 of the heat exchange unit 4 and the patient interface 8, and its structure includes an internal gas passage 71 and an external heat-insulating layer 72.

[0053] The internal gas passage 71 uses a medical-grade silicone tube with an outer diameter of 6mm, and the external insulation layer 72 uses a rubber-plastic insulation tube with an inner diameter of 6mm. Inserting the silicone tube into the rubber-plastic insulation tube effectively reduces cold loss during the low-temperature gas transportation process, and this solution is also low-cost. The air inlet of the insulation pipe 7 is connected to the air outlet 42 through a two-way straight-insertion connector to achieve a variable diameter sealing fixation, ensuring a firm connection that is not easy to fall off.

[0054] The temperature sensors include a first temperature sensor 1 and a second temperature sensor 2, both of which are high-precision thermistors. The first temperature sensor 1 is located on the side of the insulated pipe 7 near the connection to the air outlet 42, and the second temperature sensor 2 is located on the side of the insulated pipe 7 near the connection to the patient interface 8. They are used to monitor the temperature of the gas after initial cooling and the temperature of the gas actually inhaled by the patient, respectively.

[0055] Specifically, the first temperature sensor 1 is connected to the internal gas passage 71 via a Y-type tee connector 73. The straight end of the Y-type tee connector is connected to the internal gas passage, and the first temperature sensor 1 is installed in the angled branch. The sensor probe is inserted close to the inner wall of the pipe to ensure that it can fully contact the flowing gas. At the same time, the gap between the sensor and the Y-type tee connector is sealed with medical glue to ensure that there is no air leakage and that the pipe can flow normally.

[0056] The second temperature sensor 2 is connected to the internal gas passage 71 via a six-way converter 74. The two ends of the six-way converter are connected to the internal gas passage, one branch of which is connected to the patient interface 8. At least one end of the remaining branches houses the second temperature sensor 2, with the sensor probe extending close to the bottom of the pipe and in complete contact with the flowing gas. The gaps are also sealed with medical adhesive. The remaining branches of the six-way converter can serve as reserved ports for humidification or medication administration. Unused ports are sealed with medical plugs 75 to prevent leakage.

[0057] The patient interface 8 can be a disposable oxygen mask or nasal cannula, which is connected to the branch port of the six-way converter 74 through the outlet end of the insulated tubing 7 to deliver cooled gas to the patient's respiratory tract.

[0058] The control unit 6 is located inside the chassis 1 and is electrically connected to the flow regulating valve 2, the thermoelectric cooler 45, the first temperature sensor 1, the second temperature sensor 2, and the display control panel 9. The control unit 6 uses an STM32F103C8T6 microcontroller as its lower-level core, responsible for executing temperature control algorithms and device logic control. This control unit also integrates an ESP8266 WiFi module, which communicates with the microcontroller via a UART serial port to upload device operating data to the cloud.

[0059] The temperature control range of this therapeutic device is from 4℃ to room temperature (adjustable), with a control accuracy of ±0.5℃ of the set value. The time required to drop from room temperature of 25℃ to the set temperature of 16℃ does not exceed 10 minutes.

[0060] Example 2: Combination Figures 1-8 This embodiment describes a temperature control method for an inhalation-type cold air therapy device, implemented using the therapy device described in Embodiment 1 above. The method employs a PID closed-loop control algorithm and combines it with Internet of Things (IoT) technology to achieve remote data monitoring. Specifically, it includes the following steps:

[0061] Step 1: Obtain the preset target temperature value and read the current actual temperature value in real time.

[0062] The operator inputs a preset target temperature value, such as 16°C, via the control panel 9. The control unit 6 receives and stores this target value. Simultaneously, the control unit 6 reads in real-time the first temperature value collected by the first temperature sensor 1 and the second temperature value collected by the second temperature sensor 2. The first temperature value is the initial cooling temperature of the outlet 42 of the heat exchange unit 4, and the second temperature value is the inhalation temperature of the insulated tubing 7 near the patient interface 8. The second temperature value is used as the actual temperature value for closed-loop control feedback, while the first temperature value is used as an auxiliary reference to monitor the cooling response speed of the thermoelectric cooler.

[0063] Step 2: Calculate the temperature error.

[0064] The control unit 6 calculates the temperature error between the preset target temperature value and the current actual temperature value in real time. The current actual temperature value is the second temperature value, and the temperature error is the difference between the target value and the actual value.

[0065] Step 3: Use the PID control algorithm to generate control signals.

[0066] The control unit 6 uses a PID control algorithm to calculate the temperature error and generate a control signal for adjusting the cooling power of the thermoelectric cooler 45. The specific functions of the three stages of the PID algorithm are as follows:

[0067] Proportional element (P): Generates a control component that is proportional to the magnitude of the current temperature error. The larger the error, the greater the adjustment force and the faster the response speed.

[0068] Integral component (I): Accumulates historical temperature errors and generates control components to eliminate steady-state errors, ensuring that the actual temperature can be accurately stabilized at the target temperature value after long-term operation, without generating continuous deviations.

[0069] Differential component (D): Generates predictive control components based on the rate of change (i.e. trend) of temperature error, which acts as a damper to suppress temperature overshoot (overcooling) and oscillation (repeated temperature fluctuations), thus making the temperature change curve converge smoothly.

[0070] The outputs of the three stages are superimposed to form the final control signal.

[0071] Step 4: Adjust the output power of the semiconductor cooling chip according to the control signal.

[0072] Based on the control signal generated in step three, control unit 6 dynamically adjusts the start-up, shutdown, and operating power of the thermoelectric cooler 45 through the drive circuit. When the actual temperature is higher than the target temperature, the cooling power is increased; when the actual temperature is close to or lower than the target temperature, the cooling power is decreased or cooling is paused, thereby changing the cooling capacity output at the cold end.

[0073] Step 5: Repeat the feedback loop until the temperature converges within the preset accuracy range.

[0074] The first temperature sensor 1 and the second temperature sensor 2 continuously collect the actual temperature of the regulated gas and feed it back to the control unit 6 in real time. The control unit executes steps one through four in a loop until the current actual temperature value converges within ±0.5℃ of the preset target temperature value and remains stable. If the actual temperature deviates from the target temperature value by more than ±0.5℃ within a preset time period, the control unit triggers an alarm and displays the alarm information on the control panel.

[0075] Step 6: Data Upload and Remote Monitoring.

[0076] During temperature control, control unit 6 (the lower-level machine, based on STM32F103C8T6) encapsulates the collected temperature data (floating-point, unit °C) and key information such as cooling status according to the JSON protocol, generating a data packet containing data fields. After encapsulation, the STM32 sends the JSON data packet to the ESP8266 WiFi module via UART serial port, and the ESP8266 uploads the data to the device data stream specified by the OneNet cloud platform via the HTTP protocol.

[0077] The OneNet cloud platform acts as a data relay node, receiving JSON data uploaded by lower-level devices, parsing and storing the data. Data retention is supported for 7 days, and a data subscription mechanism is implemented based on the platform's device management functions. When the cloud platform receives new data from lower-level devices, it automatically triggers a push mechanism, sending the parsed temperature data and key information such as cooling status in JSON format to the subscribed upper-level devices in real time.

[0078] The host application is a cross-platform mobile app developed using JavaScript, supporting Android and iOS systems. After startup, the app establishes a long MQTT connection with the OneNet cloud platform (port 1883) via its built-in network module. After device authentication, it enters data listening mode. When it receives a JSON data packet from the cloud platform, the app parses the data fields, extracts information such as temperature and cooling status, and displays the temperature data numerically and the cooling status intuitively as icons on the UI interface, enabling remote real-time monitoring.

[0079] In summary, the temperature control method in this embodiment achieves high-precision temperature control of ±0.5℃ through a PID closed-loop algorithm. Furthermore, through hardware collaboration between STM32 and ESP8266, standardized data encapsulation using the JSON protocol, relaying via the OneNet cloud platform, and parsing and displaying via JavaScriptAPP, it realizes a complete closed-loop process for temperature control data from acquisition to terminal presentation. This method features high real-time performance, strong compatibility, and convenient operation.

[0080] It should be noted that in the above embodiments, as long as the technical solutions are not contradictory, they can be permuted and combined. Those skilled in the art can exhaust all possibilities based on the mathematical knowledge of permutation and combination. Therefore, the present invention will not describe the technical solutions after permutation and combination one by one, but it should be understood that the technical solutions after permutation and combination have been disclosed by the present invention.

[0081] The above description is merely a preferred embodiment of the present invention and is not intended to limit the invention. Various modifications and variations can be made to the present invention by those skilled in the art. Any modifications, equivalent substitutions, improvements, etc., made within the spirit and principles of the present invention should be included within the scope of protection of the present invention.

Claims

1. An inhalation-type cold air therapy device, characterized in that: The device includes a chassis (1), a flow regulating valve (2), an air inlet pipe (3), a heat exchange unit (4), a temperature sensor, a control unit (6), an insulated pipe (7), a patient interface (8), a display control panel (9), and a gas cylinder (10). The heat exchange unit (4) and the control unit (6) are installed inside the chassis (1). The display control panel (9) is installed on the front panel (1) of the chassis (1). The heat exchange unit (4) has an air inlet (41) and an air outlet (42). One end of the air inlet pipe (3) is connected to the gas cylinder (10), and the other end is connected to the air inlet (41) through the flow regulating valve (2). The patient interface (8) is connected to the air outlet (42) through the insulated pipe (7). A temperature sensor is installed on the insulated pipe (7). The control unit (6) is connected to the flow regulating valve (2), the heat exchange unit (4), the temperature sensor, and the display control panel (9) respectively.

2. The inhalation-type cold air therapy device according to claim 1, characterized in that: The heat exchange unit (4) includes an aluminum alloy flow channel block (43), a temperature-conducting coil (44), and a semiconductor cooling chip (45). The aluminum alloy flow channel block (43) has a serpentine slot for accommodating the temperature-conducting coil (44). The temperature-conducting coil (44) is embedded in the serpentine slot and fits tightly with the aluminum alloy flow channel block (43) to achieve heat conduction. The cold end face of the semiconductor cooling chip (45) is attached to the surface of the aluminum alloy flow channel block (43) with high thermal conductivity silicone grease to cool the gas flowing through the temperature-conducting coil (44) through the aluminum alloy flow channel block (43). The two ends of the temperature-conducting coil (44) are the air inlet (41) and the air outlet (42), respectively.

3. The inhalation-type cold air therapy device according to claim 2, characterized in that: The hot end face of the semiconductor cooling chip (45) is connected to a copper heat dissipation fin group (46), and an exhaust cooling fan (47) is arranged between the copper heat dissipation fin groups (46).

4. The inhalation-type cold air therapy device according to claim 3, characterized in that: The copper heat dissipation fin assembly (46) is topped with a top plate (48) that presses the copper heat dissipation fin assembly (46), the semiconductor cooling chip (45) and the aluminum alloy flow channel block (43) together, so that the cold end face of the semiconductor cooling chip (45) is tightly pressed against the aluminum alloy flow channel block (43).

5. An inhalation-type cold air therapy device according to claim 4, characterized in that: The aluminum alloy flow channel block (43) is covered with thermal insulation cotton (49), and multiple cooling fans (11) are installed on the side wall of the chassis (1) to allow the internal air to circulate.

6. The inhalation-type cold air therapy device according to claim 1, characterized in that: The temperature sensor includes a first temperature sensor (51) and a second temperature sensor (52). The first temperature sensor (51) is located on the side of the insulated pipe (7) near the connection of the air outlet (42), and the second temperature sensor (52) is located on the side of the insulated pipe (7) near the connection of the patient interface (8).

7. An inhalation-type cold air therapy device according to claim 6, characterized in that: The insulated pipeline (7) includes an internal gas passage (71) and an external insulation layer (72), with the external insulation layer (72) fitted over the internal gas passage (71).

8. An inhalation-type cold air therapy device according to claim 7, characterized in that: The first temperature sensor (51) is connected to the internal gas passage (71) through a Y-type tee (73). That is, the straight end of the Y-type tee (73) is connected to the internal gas passage (71), and the first temperature sensor (51) is installed in the inclined branch of the Y-type tee (73), so that the probe of the first temperature sensor (51) is inserted into the position close to the inner wall of the pipe of the internal gas passage (71).

9. An inhalation-type cold air therapy device according to claim 7, characterized in that: The first temperature sensor (51) is connected to the internal gas passage (71) through a six-way converter (74). That is, the two straight ends of the six-way converter (74) are connected to the internal gas passage (71). One end of the branch of the six-way converter (74) is connected to the patient interface (8), and at least one end of the other branches is equipped with a second temperature sensor (52), so that the probe of the second temperature sensor (52) is inserted into the position close to the inner wall of the pipe of the internal gas passage (71).

10. A temperature control method for an inhalation-type cold air therapy device, implemented using the therapy device according to any one of claims 2 to 9, characterized in that, include: Step 1: The control unit (6) acquires the preset target temperature value and reads the current actual temperature value collected by the temperature sensor in real time; Step 2: The control unit (6) calculates the temperature error between the target temperature value and the current actual temperature value; Step 3: The control unit (6) uses a PID control algorithm to perform proportional, integral, and derivative operations on the temperature error to generate a control signal for adjusting the cooling power of the semiconductor refrigeration chip (45). Step 4: The control unit (6) adjusts the output power of the semiconductor cooling chip (45) according to the control signal; Step 5: Repeat steps 1 to 4 until the current actual temperature value converges within the preset accuracy range of the target temperature value.

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