Intensive care medicine department breathing oxygen supply device capable of being monitored and adjusted in real time

Abstract

The invention relates to the technical field of medical breathing oxygen supply devices, in particular to an intensive care medicine department breathing oxygen supply device capable of being monitored and adjusted in real time, which comprises an oxygen supply tank, an air supply pipe is arranged at the output end of the oxygen supply tank, a small mixing tank is arranged at one end of the air supply pipe, and a humidifying pipe is arranged on the inner side of the small mixing tank. A miniature humidifier is arranged outside the small mixing tank, the output end of the miniature humidifier is connected with a humidifying pipe, a fixing frame is arranged on the inner side of the small mixing tank, a hydrophobic filter screen is arranged on the inner side of the fixing frame, a connecting pipe is arranged below the small mixing tank, and a mask is arranged at one end of the connecting pipe; the gas humidifying link is close to the patient end as much as possible, it is prevented that when flowing in a long pipeline, wet gas encounters a cold pipe wall or the environment temperature drops, water vapor is condensed into liquid water, the humidifying effect is improved, and the risk that a patient inhales by mistake is eliminated.

Description

Technical Field

[0001] This invention relates to the field of medical respiratory oxygen supply devices, and more particularly to a respiratory oxygen supply device for intensive care units that can be monitored and adjusted in real time. Background Technology

[0002] In the field of medical respiratory oxygen supply device technology, traditional respiratory oxygen supply systems usually adopt a series humidification structure, that is, the humidifier is integrated into the long gas delivery pipeline between the oxygen supply host and the patient interface; such devices heat and humidify the flowing gas through the humidifier, and then transmit the humidified gas to the patient end through a delivery pipeline several meters long.

[0003] The humidification modules of existing respiratory oxygen supply devices generally adopt a main unit built-in or external series structure, with a 0.5-2 meter gas delivery pipeline between the humidification chamber and the patient interface. Taking a typical intensive care ventilator as an example, after the compressed gas is humidified by the humidifier inside the main unit, it needs to be transmitted through multiple pipelines such as Y-tubes and extension tubes before finally reaching the patient's airway interface. This layout causes the humidified gas to continuously exchange heat with the pipeline wall during the transmission process. When the ambient temperature is lower than the gas dew point temperature, condensation will inevitably accumulate on the inner wall of the pipeline. During gas transmission, when saturated humidified gas (temperature 34-37℃, relative humidity 100%) flows through polyvinyl chloride (PVC) pipes, water vapor condenses on the pipe wall surface due to the pipe wall temperature usually being lower than the gas dew point temperature (about 31-34℃). The condensate in the pipe absorbs heat, causing the gas temperature and humidity at the end of the pipe to drop, affecting the humidification effect. Furthermore, excessively cold and dry gas can irritate the airway, reducing comfort and compliance.

[0004] Therefore, to address the aforementioned issues, a real-time monitoring and adjustment-enabled respiratory oxygen supply device for intensive care units is proposed. This device places the gas humidification stage as close as possible to the patient, preventing condensation of water vapor into liquid water when the humidified gas encounters cold pipe walls or a drop in ambient temperature during its flow through long pipelines. The humidified gas has almost no time or space to cool and condense, and because the humidification stage is close to the patient, the mixed gas reaches the airway almost directly, with virtually no condensate accumulating in the pipeline. This improves the humidification effect and eliminates the risk of aspiration. Summary of the Invention

[0005] To overcome the problems of existing humidifiers in intensive care unit respiratory oxygen supply devices using a series humidification structure, which cause gas condensation and produce condensate water, affecting the humidification effect and causing patient discomfort.

[0006] The technical solution of the present invention is as follows: a real-time monitoring and adjustment respiratory oxygen supply device for intensive care units, comprising an oxygen supply tank, an air supply pipe at the output end of the oxygen supply tank, a small mixing tank at one end of the air supply pipe, a humidification pipe inside the small mixing tank, a miniature humidifier outside the small mixing tank, the output end of the miniature humidifier and the humidification pipe being connected to each other, a fixing frame inside the small mixing tank, a hydrophobic filter inside the fixing frame, a connecting pipe below the small mixing tank, and a face mask at one end of the connecting pipe.

[0007] Preferably, dry oxygen-containing gas is supplied to a small mixing tank via an oxygen supply tank and a gas supply pipe. The gas supply pipe has a dry pipe structure. A dry miniature humidifier supplies a high-humidity supplementary gas flow to the small mixing tank via a humidification pipe. The high-humidity supplementary gas flow enters the small mixing tank tangentially, generating a high-speed rotating airflow that mixes with the dry oxygen-containing gas. The denser liquid is filtered and blocked by a hydrophobic filter. The mixed and filtered gas is then supplied to the face mask via a connecting pipe. The small mixing tank is located near the end of the face mask, where the dry oxygen-containing gas and the high-humidity supplementary gas mix rapidly, thereby humidifying the gas. The humidification process is designed to be as close to the patient as possible to prevent condensation of the humidified gas as it flows through long tubing. This avoids the condensation from absorbing heat from the gas, which could lead to a drop in gas temperature and humidity at the end of the tubing, thus affecting the humidification effect. The dry, oxygen-containing gas in this device produces almost no condensation in long tubing. Humidification occurs at the very end, leaving almost no time or space for the humidified gas to cool and condense. Furthermore, the humidification process is close to the patient, and the mixed gas reaches the airway directly, with almost no condensation accumulating in the tubing, eliminating the risk of aspiration.

[0008] Preferably, a controller is provided on one side of the miniature humidifier, and the controller is a PLC programmable controller.

[0009] Preferably, a heat-conducting gasket is fitted on the outside of the gas supply pipe, and an electric heating coil is wound around the outside of the heat-conducting gasket.

[0010] Preferably, one end of the electric heating coil is equipped with a heating power source, both ends of the electric heating pad are connected to the heating power source, and the heating power source and the controller are connected wirelessly.

[0011] Preferably, a guide pipe is provided below the fixed frame, the guide pipe passes through the side wall of the fixed frame and the small mixing tank, and a small collection tank is provided at one end of the guide pipe.

[0012] Preferably, a first connector is provided at one end of the guide tube, and a second connector is provided above the small collection tank, with the first connector and the second connector being threaded together.

[0013] Preferably, a temperature and humidity sensor body is provided on one side of the small mixing tank, a probe is provided on one side of the temperature and humidity sensor body, one end of the probe is located inside the small mixing tank, and a signal transmitter is provided above the humidity sensor body.

[0014] Preferably, the controller integrates a data receiving unit, a data preprocessing unit, a data analysis unit, and a temperature and humidity control unit. The data receiving unit is used to receive real-time gas temperature and humidity data at the outlet of the small mixing tank transmitted by the signal transmitter. The data preprocessing unit is used to filter the temperature and humidity data. The data analysis unit is used to calculate the absolute temperature difference based on the real-time temperature and humidity data, the preset target temperature, and the preset target relative temperature. The temperature and humidity control unit is used to dynamically adjust the humidification amount of the micro humidifier.

[0015] Preferably, the controller includes the following steps when performing data analysis: S101: Medical staff input target values ​​through the controller, specifically: target temperature T_target, target relative humidity RH_target, and humidity threshold m; S102: The data analysis unit converts the real-time gas humidity RH_out collected at the outlet of the small mixing tank into absolute humidity AH_out; S103: The data analysis unit calculates the target absolute humidity AH_target=f(T_target, RH_target); S104: The data analysis unit generates an error signal: ΔAH = AH_target - AH_out.

[0016] Preferably, the controller includes the following steps when dynamically adjusting the humidification level: S201: The temperature and humidity control unit performs the following humidity requirement decision based on the error signal: If |ΔAH|≤threshold m, maintain the current humidification power / amplitude; If |ΔAH| > threshold m, execute the PID control algorithm: Humidification output U(t) = K_p·ΔAH + K_i·∫ΔAH·dt + K_d·d(ΔAH) / dt; Where K_p, K_i and K_d are the proportional gain coefficient, integral gain coefficient and derivative gain coefficient in the PID control algorithm, respectively, dt is the derivative time interval and d represents the derivative operator; S202: The micro humidifier adjusts the heating power according to the output U(t) of the humidification amount.

[0017] The beneficial effects of this invention are: Dry oxygen-containing gas is supplied from the oxygen supply tank to the small mixing tank via a supply pipe. The supply pipe has a dry piping structure. A dry miniature humidifier supplies a high-humidity supplementary gas flow to the small mixing tank via a humidification pipe. The high-humidity supplementary gas enters the small mixing tank tangentially, generating a high-speed rotating airflow that mixes with the dry oxygen-containing gas. The denser liquid is filtered and blocked by a hydrophobic filter. The mixed and filtered gas is then supplied to the face mask via a connecting pipe. The small mixing tank is located near the face mask end, where the dry oxygen-containing gas and the high-humidity supplementary gas mix rapidly, thus achieving the gas humidification process. By placing the device as close to the patient as possible, it prevents the humidified gas from condensing into liquid water when it encounters colder pipe walls or a drop in ambient temperature during its flow through long pipelines. This avoids the problem of liquid condensate absorbing heat from the gas, causing a drop in gas temperature and humidity at the end of the pipeline, which would affect the humidification effect. The dry oxygen-containing flow of this device produces almost no condensate in long pipelines. Humidification occurs at the very end, and the humidified gas has almost no time or space to cool and condense. Furthermore, since the humidification stage is close to the patient, the mixed gas reaches the airway directly, with almost no condensate accumulating in the pipeline, eliminating the risk of aspiration. Attached Figure Description

[0018] Figure 1 The diagram shown is a first three-dimensional structural schematic of the real-time monitoring and adjustment-enabled respiratory oxygen supply device for intensive care units according to the present invention. Figure 2 The diagram shown is a second three-dimensional structural schematic of the real-time monitoring and adjustment-enabled respiratory oxygen supply device for intensive care units according to the present invention. Figure 3 The diagram shown is a three-dimensional cross-sectional view of the intensive care unit respiratory oxygen supply device with real-time monitoring and adjustment according to the present invention. Figure 4 The diagram shown is a partial cross-sectional view of the intensive care unit respiratory oxygen supply device with real-time monitoring and adjustment according to the present invention. Figure 5 The diagram shown is a partial planar three-dimensional structural schematic of the real-time monitoring and adjustment-enabled respiratory oxygen supply device for intensive care units according to the present invention. Figure 6 The diagram shown is a partial three-dimensional structural schematic of the real-time monitoring and adjustment-enabled respiratory oxygen supply device for intensive care units according to the present invention. Explanation of reference numerals in the attached drawings: 1. Oxygen supply tank; 2. Gas supply pipe; 3. Small mixing tank; 4. Humidification pipe; 5. Miniature humidifier; 6. Fixture; 7. Hydrophobic filter; 8. Connecting pipe; 9. Mask; 101. Controller; 201. Thermally conductive gasket; 202. Electric heating coil; 203. Heating power supply; 301. Guide pipe; 302. First connector; 303. Small collection tank; 304. Second connector; 401. Humidity sensor body; 402. Detector head; 403. Signal transmitter. Detailed Implementation

[0019] The present invention will be further described below with reference to the accompanying drawings and embodiments.

[0020] Please see Figure 1 and Figure 2 This invention provides an embodiment of a real-time monitorable and adjustable intensive care unit respiratory oxygen supply device, comprising an oxygen supply tank 1, an air supply pipe 2 at the output end of the oxygen supply tank 1, a small mixing tank 3 at one end of the air supply pipe 2, a humidification pipe 4 inside the small mixing tank 3, a miniature humidifier 5 outside the small mixing tank 3, the output end of the miniature humidifier 5 being connected to the humidification pipe 4, a fixing frame 6 inside the small mixing tank 3, a hydrophobic filter 7 inside the fixing frame 6, a connecting pipe 8 below the small mixing tank 3, and a face mask 9 at one end of the connecting pipe 8. Dry oxygen-containing gas is input from the oxygen supply tank 1 to the small mixing tank 3 via the air supply pipe 2. The air supply pipe 2 has a dry pipe structure, and the dry miniature humidifier 5 is connected to the small mixing tank 3 via the air supply pipe 2. High-humidity supplementary airflow is input into the small mixing tank 3 via the humidification tube 4. The high-humidity supplementary airflow enters the small mixing tank 3 tangentially, generating a high-speed rotating airflow that mixes with the dry oxygen-containing gas. The denser liquid is filtered and blocked by the hydrophobic filter 7. The mixed and filtered gas is input into the mask 9 via the connecting tube 8. The small mixing tank 3 is located near the end of the mask 9. The dry oxygen-containing gas and the high-humidity supplementary gas mix rapidly here, so that the gas humidification process is as close to the patient's end as possible. This prevents the humidified gas from encountering colder pipe walls or a drop in ambient temperature when flowing in a long pipeline, which would cause water vapor to condense into liquid water. It also avoids the problem of liquid condensate absorbing heat from the gas, causing a drop in gas temperature and humidity at the end of the pipeline, which would affect the humidification effect.

[0021] Please see Figure 3 and Figure 4 In this embodiment, a controller 101 is provided on one side of the miniature humidifier 5. The controller 101 is a PLC programmable controller 101. A thermally conductive gasket 201 is sleeved on the outside of the air supply pipe 2. An electric heating coil 202 is wound around the outside of the thermally conductive gasket 201. In use, the electric heating coil 202 is energized and releases heat to heat the thermally conductive gasket 201. The thermally conductive gasket transfers heat to the gas transported inside the air supply pipe 2. A heating power supply 203 is provided at one end of the electric heating coil 202. The two ends of the electric heating gasket and the heating power supply 203 are connected to each other. The heating power supply 203 and the controller 101 are connected wirelessly. In use, the controller 101 controls the power input from the heating power supply 203 to the electric heating coil 202, thereby controlling the temperature of the electric heating coil 202 and keeping the gas in the air supply pipe 2 within the range of 34℃~37℃.

[0022] Please see Figure 5 and Figure 6In this embodiment, a guide pipe 301 is provided below the fixing frame 6, and the guide pipe 301 penetrates the side wall of the fixing frame 6 and the small mixing tank 3. A small collection tank 303 is provided at one end of the guide pipe 301. In use, the liquid filtered by the hydrophobic filter 7 is introduced into the small collection tank 303 along the guide pipe 301. A first connector 302 is provided at one end of the guide pipe 301, and a second connector 304 is provided above the small collection tank 303. The first connector 302 and the second connector 304 are threadedly connected. In use, the small collection tank 303 can be quickly disassembled and assembled through the threaded connection between the first connector 302 and the second connector 304, thereby facilitating the cleaning of the filtered liquid. A temperature and humidity sensor body 401 is provided on one side of the small mixing tank 3, and a probe 402 is provided on one side of the temperature and humidity sensor body 401. One end of the probe 402 is located inside the small mixing tank 3. A signal transmitter 403 is installed above the humidity sensor body 401. In use, the probe 402 detects the temperature and humidity of the gas at the outlet of the small mixing tank 3, and the signal transmitter 403 transmits the collected real-time temperature and humidity signals to the controller 101. The controller 101 integrates a data receiving unit, a data preprocessing unit, a data analysis unit, and a temperature and humidity control unit. The data receiving unit receives the real-time gas temperature and humidity data at the outlet of the small mixing tank 3 transmitted by the signal transmitter 403. The data preprocessing unit filters the temperature and humidity data. The data analysis unit calculates the absolute temperature difference based on the real-time temperature and humidity data, the preset target temperature, and the preset target relative temperature. The temperature and humidity control unit dynamically adjusts the humidification amount of the micro humidifier 5.

[0023] The controller 101 performs the following steps when conducting data analysis: S101: Medical staff input target values ​​through controller 101, specifically: target temperature T_target, target relative humidity RH_target, and humidity threshold m; S102: The data analysis unit converts the real-time gas humidity RH_out collected at the outlet of the small mixing tank 3 into absolute humidity AH_out; S103: The data analysis unit calculates the target absolute humidity AH_target=f(T_target, RH_target); S104: The data analysis unit generates an error signal: ΔAH = AH_target - AH_out.

[0024] The controller 101 performs the following steps when dynamically adjusting the humidification level: S201: The temperature and humidity control unit performs the following humidity requirement decision based on the error signal: If |ΔAH|≤threshold m, maintain the current humidification power / amplitude; If |ΔAH| > threshold m, execute the PID control algorithm: Humidification output U(t) = K_p·ΔAH + K_i·∫ΔAH·dt + K_d·d(ΔAH) / dt; Where K_p, K_i and K_d are the proportional gain coefficient, integral gain coefficient and derivative gain coefficient in the PID control algorithm, respectively, dt is the derivative time interval and d represents the derivative operator; S202: The micro humidifier 5 adjusts the heating power according to the output U(t) of the humidification amount.

[0025] During operation, first connect the output end of oxygen supply tank 1 to air supply pipe 2, ensuring that air supply pipe 2 is a dry pipe structure; connect the other end of air supply pipe 2 to the air inlet of small mixing tank 3, and insert the humidification pipe 4 of micro humidifier 5 tangentially into the humidification inlet on the side wall of small mixing tank 3, so that the humidified airflow enters the tank in a spiral shape; install hydrophobic filter screen 7 in the fixing frame 6 inside small mixing tank 3, ensuring that the filter screen is tightly attached to the inner wall of the tank to intercept droplets; connect one end of guide pipe 301 through the first connector 3 02 is connected to the bottom of the fixed frame 6, and the other end is threaded to the small collection tank 303 through the second connector 304 to form a condensate outlet path; one end of the connecting pipe 8 is connected to the air outlet of the small mixing tank 3, and the other end is connected to the mask 9 to complete the gas delivery path construction; finally, the probe 402 of the temperature and humidity sensor body 401 is inserted into the reserved hole on the side wall of the small mixing tank 3 to ensure that the probe end is located at the outlet of the mixed airflow, and a wireless communication connection is established with the controller 101 through the signal transmitter 403; During operation, oxygen supply tank 1 supplies dry oxygen-containing gas at a temperature controlled between 34°C and 37°C to small mixing tank 3 via gas supply pipe 2. The gas is precisely temperature-controlled as it flows through the heat-conducting gasket 201 heated by electric heating coil 202. Simultaneously, miniature humidifier 5 heats and vaporizes purified water, generating a high-humidity supplementary airflow that is tangentially injected into small mixing tank 3 via humidification pipe 4, forming a rotating airflow that is fully mixed with the dry gas. During the mixing process, hydrophobic filter 7 intercepts denser liquid water droplets, and the intercepted condensate flows into small collection tank 303 along guide pipe 301. The mixed warm and humid gas is then delivered to mask 9 via connecting pipe 8. Because the humidification process is close to the patient's end, the gas stays in the pipeline for a very short time, effectively avoiding the condensation problem caused by traditional long pipeline transmission. Medical staff can preset the target temperature T_target (34°C~37°C) and target relative humidity RH_target (80%~100%) via controller 101, and set the humidity threshold m (usually ±5%RH). The temperature and humidity sensor body 401 continuously collects gas temperature and humidity data at the outlet of the small mixing tank 3. The data is transmitted in real time to the controller 101 via the signal transmitter 403. The controller 101 has an embedded algorithm that performs the following operations: First, the raw signal is filtered and denoised by the data preprocessing unit. Then, the relative humidity RH_out is converted into absolute humidity AH_out and compared with the target absolute humidity AH_target (calculated from T_target and RH_target) to generate an error ΔAH. If |ΔAH|≤ threshold m, the current humidification is maintained. Power; if |ΔAH|>threshold m, then the PID control algorithm is activated to calculate the humidification output U(t), and the heating power or ultrasonic amplitude of the micro humidifier 5 is dynamically adjusted; for example, when the actual humidity is detected to be lower than the target value, the controller 101 increases the humidifier power to increase the humidification; otherwise, the power is reduced; the power supply of the electric heating coil 202 is also synchronously adjusted by the controller 101 to ensure that the gas temperature in the gas supply pipe 2 is constant; medical staff can periodically unscrew the second connector 304 of the small collection tank 303 to clean the accumulated condensate and ensure the continuous and stable operation of the system.

[0026] Through the above steps, dry oxygen-containing gas is fed into the small mixing tank 3 via the supply pipe 2 from the oxygen supply tank 1. The supply pipe 2 has a dry pipe structure. The dry miniature humidifier 5 feeds high-humidity supplementary airflow into the small mixing tank 3 via the humidification pipe 4. The high-humidity supplementary airflow enters the small mixing tank 3 tangentially, generating a high-speed rotating airflow that mixes with the dry oxygen-containing gas. The denser liquid is filtered and blocked by the hydrophobic filter 7. The mixed and filtered gas is fed into the mask 9 via the connecting pipe 8. The small mixing tank 3 is located near the end of the mask 9, where the dry oxygen-containing gas and the high-humidity supplementary gas mix rapidly. This design places the gas humidification stage as close to the patient as possible, preventing the humidified gas from condensing into liquid water when it encounters colder pipe walls or a drop in ambient temperature during its flow through long pipelines. It also avoids the problem of liquid condensate absorbing heat from the gas, causing a drop in gas temperature and humidity at the end of the pipeline, thus affecting the humidification effect. The dry, oxygen-containing flow of this device produces almost no condensate in long pipelines. Humidification occurs at the very end, leaving almost no time or space for the humidified gas to cool and condense. Furthermore, the humidification stage is close to the patient, and the mixed gas reaches the airway directly, with almost no condensate accumulating in the pipeline, eliminating the risk of aspiration.

[0027] The embodiments of the present invention have been described in detail above with reference to the accompanying drawings. However, the present invention is not limited to the above embodiments. Within the scope of knowledge possessed by those skilled in the art, various changes can be made without departing from the spirit of the present invention.

Claims

1. A real-time monitorable and adjustable respiratory oxygen supply device for intensive care units, comprising an oxygen supply tank (1), characterized in that: An air supply pipe (2) is provided at the output end of the oxygen supply tank (1). A small mixing tank (3) is provided at one end of the air supply pipe (2). A humidification pipe (4) is provided inside the small mixing tank (3). A miniature humidifier (5) is provided outside the small mixing tank (3). The output end of the miniature humidifier (5) and the humidification pipe (4) are connected to each other. A fixing frame (6) is provided inside the small mixing tank (3). A hydrophobic filter screen (7) is provided inside the fixing frame (6). A connecting pipe (8) is provided below the small mixing tank (3). A mask (9) is provided at one end of the connecting pipe (8).

2. The intensive care unit respiratory oxygen supply device with real-time monitoring and adjustment according to claim 1, characterized in that: A controller (101) is provided on one side of the miniature humidifier (5), and the controller (101) is a PLC programmable controller (101).

3. The intensive care unit respiratory oxygen supply device with real-time monitoring and adjustment according to claim 2, characterized in that: A heat-conducting gasket (201) is fitted on the outside of the gas supply pipe (2), and an electric heating coil (202) is wound around the outside of the heat-conducting gasket (201).

4. The intensive care unit respiratory oxygen supply device with real-time monitoring and adjustment according to claim 3, characterized in that: A heating power supply (203) is provided at one end of the electric heating coil (202), and the two ends of the electric heating pad are connected to the heating power supply (203). The heating power supply (203) and the controller (101) are connected by wireless signal.

5. The intensive care unit respiratory oxygen supply device with real-time monitoring and adjustment according to claim 1, characterized in that: A guide pipe (301) is provided below the fixed frame (6). The guide pipe (301) passes through the side wall of the fixed frame (6) and the small mixing tank (3). A small collection tank (303) is provided at one end of the guide pipe (301).

6. A real-time monitoring and adjustable intensive care unit respiratory oxygen supply device according to claim 5, characterized in that: A first connector (302) is provided at one end of the guide pipe (301), and a second connector (304) is provided above the small collection tank (303). The first connector (302) and the second connector (304) are threaded together.

7. The intensive care unit respiratory oxygen supply device with real-time monitoring and adjustment according to claim 1, characterized in that: A temperature and humidity sensor body (401) is provided on one side of the small mixing tank (3), and a probe (402) is provided on one side of the temperature and humidity sensor body (401). One end of the probe (402) is located inside the small mixing tank (3), and a signal transmitter (403) is provided above the humidity sensor body (401).

8. A real-time monitoring and adjustable intensive care unit respiratory oxygen supply device according to claim 2, characterized in that: The controller (101) integrates a data receiving unit, a data preprocessing unit, a data analysis unit, and a temperature and humidity control unit. The data receiving unit is used to receive real-time gas temperature and humidity data at the outlet of the small mixing tank (3) transmitted by the signal transmitter (403). The data preprocessing unit is used to filter the temperature and humidity data. The data analysis unit is used to calculate the absolute temperature difference based on the real-time temperature and humidity data, the preset target temperature, and the preset target relative temperature. The temperature and humidity control unit is used to dynamically adjust the humidification amount of the micro humidifier (5).

9. A real-time monitoring and adjustable intensive care unit respiratory oxygen supply device according to claim 8, characterized in that: The controller (101) performs the following steps when conducting data analysis: S101: Medical staff input target values ​​through the controller (101), specifically: target temperature T_target, target relative humidity RH_target, and humidity threshold m; S102: The data analysis unit converts the real-time gas humidity RH_out at the outlet of the small mixing tank (3) into absolute humidity AH_out; S103: The data analysis unit calculates the target absolute humidity AH_target=f(T_target, RH_target); S104: The data analysis unit generates an error signal: ΔAH = AH_target - AH_out.

10. A real-time monitoring and adjustable intensive care unit respiratory oxygen supply device according to claim 8, characterized in that: The controller (101) includes the following steps when performing dynamic humidification adjustment: S201: The temperature and humidity control unit performs the following humidity requirement decision based on the error signal: If |ΔAH|≤threshold m, maintain the current humidification power / amplitude; If |ΔAH| > threshold m, execute the PID control algorithm: Humidification output U(t) = K_p·ΔAH + K_i·∫ΔAH·dt + K_d·d(ΔAH) / dt; Where K_p, K_i and K_d are the proportional gain coefficient, integral gain coefficient and derivative gain coefficient in the PID control algorithm, respectively, dt is the derivative time interval and d represents the derivative operator; S202: Miniature humidifier (5) adjusts the heating power according to the output U(t) of the humidification amount.

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