A device for detecting pulmonary lobe ventilation function

Abstract

Disclosed is a pulmonary lobe ventilation function detection device, comprising a patient interface subsystem, a central control and information processing subsystem, a human-computer interaction subsystem and a power supply subsystem; the patient interface subsystem can block the patient's target bronchus through a bronchial balloon catheter to isolate the selected pulmonary lobe, so that the patient can inhale a certain amount of 3 He / O2 mixed gas, and can collect the patient's airway inspiratory pressure, airway exhaled gas flow, exhaled gas CO2 and O2 component data, and send them to the central control and information processing subsystem; the central control and information processing subsystem can receive the airway pressure flow of the isolated lobe and the CO2 and O2 component information of the target lobe's exhaled gas, evaluate the ventilation status of the isolated lobe and send it to the human-computer interaction subsystem for display. It can detect the flow and pressure changes of the exhaled airflow of the blocked target lobe, and can also analyze the exhaled airflow components and their changes, so as to evaluate whether the target lobe has bypass ventilation with the adjacent lobe and the target lobe's gas exchange capacity.

Description

[0001] Related Applications

[0002] This application claims priority to Chinese patent application No. 202110438231.0, filed on April 22, 2021, entitled “A device for detecting pulmonary lobe ventilation and gas exchange function”, the entire contents of which are incorporated by reference into the application herein. Technical Field

[0003] The present invention relates to a device for detecting the ventilation and gas exchange function of a lung lobe, in particular to a device for evaluating the ventilation and gas exchange conditions of a lung lobe in an isolated state / ventilated state, and a method for using the device. Background Art

[0004] Pulmonary bypass ventilation refers to a pathological physiological phenomenon of communication between pulmonary lobes, that is, a phenomenon in which ventilation occurs through a pathway outside the normal alveolar airway. The prior art generally uses the following detection methods for pulmonary bypass ventilation.

[0005] Airflow obstruction method: For example, U.S. patent application publication US2003 / 0051733A1, a catheter with a blocking component at the end is embedded in the opening of the lobar bronchus, and the catheter is connected to an instrument for measuring pressure and flow. After the bronchus is blocked, when there is no bypass ventilation, the airflow at the end of the balloon gradually decreases to zero over time, and the resistance increases; when there is bypass ventilation, the end of the balloon can continuously detect the existence of airflow. In theory, this method can accurately detect whether bypass ventilation exists, but in actual application, airway secretions have a great influence on the accurate measurement of gas flow, and respiratory movement also affects the degree of airway closure by the airbag. Therefore, it is difficult for some patients to use this method to determine whether bypass ventilation exists.

[0006] Xenon-enhanced dynamic dual-energy CT method: After the patient inhales xenon, the xenon distribution intensity is low and the enhancement time is long in the obstructed area without bypass ventilation under thin-layer CT; the xenon enhancement time is similar to that of the unobstructed area in the obstructed area with bypass ventilation. This method requires special CT equipment and is expensive.

[0007] HRCT method: For example, US patent application publication US2003 / 0055331A1 uses high-resolution CT equipment (HRCT) for imaging, which can fully display the horizontal fissures and interlobar fissures. However, due to resolution limitations, the interlobar fissures of some patients are not clearly displayed and the sensitivity is low.

[0008] Therefore, there is a clinical need for a device and method for detecting the ventilation status of pulmonary bypass that is easy to operate and can measure accurately. Summary of the invention

[0009] The purpose of the present invention is to provide a device for detecting the ventilation function of lung lobes, so as to improve the detection efficiency and the detection effect.

[0010] The technical solution of the present invention is as follows.

[0011] A pulmonary lobe ventilation function detection device comprises a patient interface subsystem, a central control and information processing subsystem, a human-computer interaction subsystem, and a power supply subsystem;

[0012] The patient interface subsystem can block the patient's target bronchus to isolate the selected lung lobe, allowing the patient to inhale a fixed amount of 3 He and O2 mixed gas, and can collect the patient's airway inspiratory pressure, airway exhaled gas flow, exhaled gas CO2 and O2 component data, and send them to the central control and information processing subsystem;

[0013] The central control and information processing subsystem is connected to the patient interface subsystem and the human-computer interaction subsystem, thereby being able to start / stop lobe ventilation function detection, receive airway pressure flow of the isolated lobe and carbon dioxide and oxygen component information of the exhaled gas of the target lobe, evaluate the ventilation status of the isolated lobe and send it to the human-computer interaction subsystem for display; alternatively, the change in gas concentration at the bronchial orifice of the target lobe can be directly evaluated through the negative pressure bypass system.

[0014] The human-computer interaction subsystem is used for the operator to input / query patient information, send start / stop pulmonary lobe ventilation function detection instructions to the central control and information processing subsystem, and graphically display the evaluation information of the isolated pulmonary lobe;

[0015] The power subsystem is connected to the mains power supply, and is also electrically connected to the patient interface subsystem, the central control and information processing subsystem, and the human-computer interaction subsystem, so as to provide working power.

[0016] Preferably, the patient interface subsystem includes a main controller unit, a communication unit, an air circuit control unit, a flow monitoring unit, a pressure detection unit, a breathing detection unit, a data storage unit, a CO2 detection unit and an O2 detection unit.

[0017] Preferably, the main controller unit is connected to the communication unit, the air circuit control unit, the flow monitoring unit, the pressure detection unit, the data storage unit, and the breathing detection unit; it is capable of receiving the start / stop ventilation check instruction sent by the central control and information processing subsystem through the communication unit, controlling the air circuit control unit to close / open the respiratory / inspiratory airway, receiving real-time data from the flow detection unit and the pressure detection unit, storing them in the data storage unit, and uploading the real-time pressure and flow data to the central control and information processing subsystem through the communication unit.

[0018] Preferably, the air path control unit comprises an inhalation valve V1 and an exhalation valve V2; the inhalation valve V1 is used to close / open the inhalation duct, and the exhalation valve V2 is used to close / open the exhalation duct.

[0019] Preferably, the central control and information processing subsystem is capable of sending instructions to the main controller unit, thereby controlling the patient interface subsystem to enter the expiratory flow and inspiratory pressure data collection phase of the selected lung lobe under normal breathing conditions;

[0020] During the data collection stage, the breathing detection unit samples the flow sensor at a certain sampling time interval, filters the sampled data and stores it in the flow signal array, and obtains the flow curve by real-time fitting; when the slope of the fitted flow curve is greater than a certain threshold and the flow is greater than a certain preset value, it is determined that the patient has an inhalation or exhalation action.

[0021] Preferably, when the patient is in the inhalation phase, the inhalation valve V1 is opened, the exhalation valve V2 is closed, and the gas inhaled by the patient enters the selected lung lobe from the inhalation port through the inhalation valve V1;

[0022] When the patient is in the exhalation phase, the exhalation valve V2 opens and the inhalation valve V1 closes. The gas exhaled by the patient passes through the exhalation valve V2 and is input into the CO2 detection unit and O2 detection unit connected in series for gas component analysis. The analysis data is uploaded to the central control and information processing subsystem.

[0023] Preferably, the central control and information processing subsystem is capable of sending instructions to the main controller unit, thereby controlling the patient interface subsystem to enter an evaluation working state, during which the inhalation valve V1 is closed;

[0024] During the evaluation working state, the breathing detection unit samples the pressure sensor at a certain sampling time interval, filters the sampled data and stores it in the pressure signal array, and obtains the pressure curve by real-time fitting;

[0025] When the slope of the pressure curve is greater than a certain threshold and the pressure is greater than a certain preset value, it is determined that the patient has an exhalation action;

[0026] At the beginning of the exhalation phase, the breathing detection unit samples the flow sensor at a certain sampling time interval, filters the sampled data and stores it in the flow signal array, and obtains the flow curve by real-time fitting;

[0027] When the slope of the flow curve is greater than a certain threshold and the flow rate is greater than a certain preset value, it is determined that the patient has an inhalation action.

[0028] Preferably, when the patient is in the exhalation state, the exhalation valve V2 is opened, and the gas exhaled by the patient is input into the CO2 sensor and the O2 sensor connected in series through the exhalation valve V2 for gas component analysis, and the analysis data is uploaded to the central control and information processing subsystem 3;

[0029] When the patient is in the inhalation state, the exhalation valve V2 is closed to prohibit external gas from entering the selected lung lobe. The central control system can achieve continuous negative pressure bypass and continuously collect the gas concentration level of the target lung bronchial opening.

[0030] Preferably, the central control and information processing subsystem evaluates the ventilation status of the isolated lung lobe including: if the concentration of O2 and CO2 in the exhaled air drops rapidly, it is determined that bypass ventilation exists in the selected lung lobe.

[0031] Preferably, the central control and information processing subsystem is also used to establish and maintain a patient database to store the patient's isolated lung lobe assessment information.

[0032] The present invention utilizes 3 The superfluid effect of He was used to evaluate the ventilation function of the lung lobe. The target bronchus was blocked with a balloon catheter in advance. Then, the subjects inhaled a fixed volume of He. 3 He and oxygen (O2) mixed gas, due to 3 He is different from 4 He has a superfluid effect and can diffuse to the entire lung within a few seconds to more than ten seconds. If there is bypass ventilation in the target lobe that is blocked by the balloon, 3 Since He is not absorbed by the blood, it can quickly enter the blocked target lobe through the bypass and then be exhaled, causing the concentration of O2 and CO2 in the exhaled air to drop rapidly. In addition to detecting the flow rate and pressure changes of the exhaled airflow when the balloon catheter blocks the target lobe, this system can also analyze whether there is any mixture of He in the exhaled airflow. 3 He; thus evaluating whether there is bypass ventilation between the target lobe and the adjacent lobe, which may be faster and have better sensitivity and specificity than the traditional lung HRCT analysis of interlobar fissure integrity to evaluate the presence of bypass ventilation or simply detecting the expiratory airflow flow and airflow resistance changes to evaluate the presence of bypass ventilation. In addition, by real-time detection of the O2 and CO2 concentrations at the target bronchial orifice during spontaneous breathing, the ventilation function of the lung segment it controls can be evaluated. At the same time, it can also be used to find the bronchi controlled by the bronchopleural fistula point. For example, under closed chest drainage, the CO2 level at the level of the controlled bronchial orifice decreases; at the same time, after connecting negative pressure suction, it can be quickly detected. BRIEF DESCRIPTION OF THE DRAWINGS

[0033] Figure 1 It is a schematic diagram of the structure of the device for detecting the ventilation and gas exchange function of the lung lobe of the present invention;

[0034] Figure 2It is a schematic diagram of the functional modules of the device for detecting the ventilation and gas exchange function of the lung lobe of the present invention;

[0035] Figure 3 It is a schematic diagram of the functional modules of the patient interface subsystem in the system of the present invention;

[0036] Figure 4 for Figure 3 Schematic diagram of the patient interface subsystem structure;

[0037] Figure 5 for Figure 3 The collection circuit schematic diagram of the flow sensor in FIG.

[0038] Figure 6 for Figure 3 The principle diagram of the acquisition circuit of the pressure sensor in FIG.

[0039] Figure 7 It is a schematic diagram of the central control and information processing subsystem in the system of the present invention.

[0040] The meanings of the reference numerals in the figures are as follows:

[0041] 1. Pulmonary lobe ventilation function detection device; 2. MCU microcontroller; 3. Central control and information processing subsystem; 4. Human-computer interaction subsystem; 5. Flow sensor; 6. Pressure sensor; 7. Inhalation valve V1; 8. Exhalation valve V2; 9. CO2 sensor; 10. O2 sensor. DETAILED DESCRIPTION

[0042] See also Figure 1-2 The structure of the pulmonary lobe ventilation function detector system includes a power supply subsystem, which provides power for the entire system; a central control and information processing subsystem, which is the core subsystem of the detector; connected to the human-computer interaction subsystem and the patient interface subsystem; the human-computer interaction subsystem is responsible for uploading the user's input control instructions to the central control and information processing subsystem, and the central control and information processing subsystem completes the user's task requirements: such as starting the patient interface subsystem to perform pulmonary lobe assessment, patient history assessment information query and other functions; the patient interface subsystem is responsible for completing the assessment instructions issued by the central control and information processing subsystem, and uploading the airway inspiratory pressure, airway exhaled gas flow, exhaled gas CO2 and O2 component data collected by this subsystem to the central control and information processing subsystem. The central control and information processing subsystem can also directly evaluate the changes in gas concentration at the bronchial orifice of the target lung lobe through the negative pressure bypass system.

[0043] like Figure 3-4As shown, the patient interface subsystem includes a main controller unit, a gas mass flow sensor, an airway pressure sensor, an inhalation solenoid valve, an exhalation solenoid valve, a CO2 sensor, and an O2 sensor. The patient interface subsystem is connected to the central control and information processing subsystem 3, thereby being able to detect the inhalation airway pressure and exhalation gas flow information of the isolated lung lobe, the carbon dioxide and oxygen components of the exhaled gas of the isolated lung lobe, and the inhalation airway pressure and exhalation gas flow information of the isolated lung lobe in real time. 3 The changes in CO2 and O2 components of the exhaled gas after He and oxygen (O2) are mixed, and the real-time concentration changes of CO2 and O2 at the target bronchial orifice during spontaneous breathing are sent to the central control and information processing subsystem 3.

[0044] Figure 5 The flow collection circuit of the gas flow sensor 5 is shown, and the flow sensor 5 has a forward and reverse bidirectional flow collection function. The flow collection circuit includes a flow sensor AWM3303V and an operational amplifier LMV324 (product model). Those skilled in the art can understand that the implementation form of the flow collection circuit is not limited to this, and any applicable flow collection circuit in the prior art can be applied to the present invention.

[0045] Figure 6 The pressure acquisition circuit of the airway pressure sensor 6 is shown. The pressure acquisition circuit includes a pressure sensor HSCSAAN001PDAA5 and an operational amplifier LMV324 (product model). Those skilled in the art will appreciate that the implementation form of the pressure acquisition circuit is not limited thereto, and any applicable pressure acquisition circuit in the prior art can be applied to the present invention.

[0046] like Figure 7 As shown, the central control and information processing subsystem includes: a power supply unit, a human-machine interaction interface unit, a central processing unit, a data storage unit and a communication unit, wherein the central processing unit is configured with evaluation system management software.

[0047] The central processing unit is connected to the human-computer interaction interface unit, the communication unit, and the data storage unit, thereby receiving instructions from the operator through the human-computer interaction subsystem, storing patient information in the data storage unit, starting / stopping the evaluation of the isolated lung lobe through the communication unit, and sending patient information and detection information to the human-computer interaction subsystem.

[0048] The human-machine interaction interface unit is connected to the central processing unit and the human-machine interaction subsystem, and is used to send operator instructions to the central processing unit hardware system and detection system management software, and to send patient information and detection information to the human-machine interaction subsystem.

[0049] The data storage unit is connected to the central processing unit and is used to store patient information and detection information.

[0050] The following describes in detail the working process of the device for detecting the ventilation and gas exchange function of the lung lobe according to the present invention.

[0051] Step 1: The patient breathes air or helium-oxygen mixture; a balloon catheter is used to occlude the target bronchus.

[0052] Step 2: The human-computer interaction subsystem 4 sends the start evaluation instruction from the user to the central control and information processing subsystem 3, and the central control and information processing subsystem 3 transmits the instruction to the MCU microcontroller through the serial port. The MCU microcontroller 2 controls the patient interface subsystem to start the evaluation workflow.

[0053] Enter the stage of collecting data of the expiratory flow and inspiratory pressure of the selected lung lobe under normal breathing state. In this stage, the data collection time is about 10 seconds, during which the patient's respiratory phase is monitored, and the MCU microcontroller 2 samples the flow sensor 5 at a certain sampling time interval, such as 100 microseconds.

[0054] The MCU microcontroller filters the sampled data, such as a sliding average filter method, and stores it in a flow signal array, such as an array of 20 elements. The MCU microcontroller 2 fits the shape of the flow signal in real time. In a preferred embodiment, the fitting adopts the least squares method to fit the flow curve y1=b1*x+b0, where y1 is the fitted flow curve, x is the sampling time, b1 is the slope of the fitted flow curve, and b0 is the initial value of the fitted flow curve. When the slope of the flow curve b1 is greater than a certain threshold and the flow rate is greater than a certain preset value, it is determined that the patient has an inhalation or exhalation action, and the patient is in an inhalation / exhalation state at this time. In a preferred embodiment, different levels of thresholds can be set according to different sensitivities, such as 0.2, 0.3 or 0.4. When the patient is in the inhalation phase, the inhalation valve V1 is opened and the exhalation valve V2 is closed, and the gas inhaled by the patient enters the patient's lung lobe from the inhalation port through the inhalation valve V1; when the patient is in the exhalation phase, the exhalation valve V2 is opened and the inhalation valve V1 is closed, and the gas exhaled by the patient passes through the exhalation valve V2 and is input into the CO2 sensor 9 and the oxygen concentration sensor 10 connected in series for gas component analysis, and the analysis data is uploaded to the central control and information processing subsystem 3. In the process of collecting expiratory flow and inhalation pressure data under normal breathing conditions, the MCU microcontroller 2 collects airway expiratory flow and inhalation pressure data in real time with a sampling time of 1 millisecond, and uploads it to the central control and information processing subsystem 3, and the central control and information processing subsystem 3 processes the data and displays it on the display interface of the human-computer interaction subsystem 4, and stores the data in the data storage of the central control and information processing subsystem 3.

[0055] Step 2: After the collection of the expiratory flow and inspiratory pressure information of the selected lung lobe under normal breathing conditions is completed, the evaluation working state is entered, during which the inspiratory valve V1 is closed.

[0056] During this period, the patient's respiratory phase is monitored, and the MCU microcontroller 2 samples the pressure sensor 6 at a certain sampling time interval, such as 100 microseconds. For specific acquisition circuits, see Figure 5 . The sampled data is filtered, such as by a sliding average filter, and stored in a pressure signal array, such as an array of 20 elements. The main controller unit uses the collected data to fit the shape of the pressure signal in real time. In a preferred embodiment, the main controller unit uses the least squares method to fit the pressure curve y2=b3*x+b2, where y2 is the fitted pressure curve, x is the sampling time, b3 is the slope of the fitted pressure curve, and b2 is the initial value of the fitted pressure curve.

[0057] When the slope b1 of the pressure curve is greater than a certain threshold and the pressure is greater than a certain preset value, it is determined that the patient has an exhalation action. In a preferred embodiment, different levels of thresholds can be set according to different sensitivities, such as 0.2, 0.3 or 0.4. When the patient is in the exhalation state, the exhalation valve V2 is opened, and the gas exhaled by the patient passes through the exhalation valve V2 and is input into the CO2 sensor 9 and O2 sensor 10 connected in series for gas component analysis, and the analysis data is uploaded to the central control and information processing subsystem 3. At the beginning of the exhalation phase, the MCU microcontroller 2 samples the flow sensor 5 at a certain sampling time interval, such as 100 microseconds. The flow sensor 5 has a forward and reverse bidirectional flow collection function.

[0058] The sampled data is filtered, such as by a sliding average filter, and stored in a flow signal array, such as an array of 20 elements. The main controller unit fits the flow signal shape in real time. In a preferred embodiment, the main controller unit uses the least squares method to fit the flow curve y1=b1*x+b0, where y1 is the fitted flow curve, x is the sampling time, b1 is the slope of the fitted flow curve, and b0 is the initial value of the fitted flow curve.

[0059] When the slope b1 of the flow curve is greater than a certain threshold and the flow rate is greater than a certain preset value, it is determined that the patient has an inhalation action. In a preferred embodiment, different levels of thresholds can be set according to different sensitivities, such as 0.2, 0.3 or 0.4. When the patient is in the inhalation state, the exhalation valve V2 is closed to prohibit external gas from entering the selected lung lobe for evaluation. During the evaluation process, the airway expiratory flow and inspiratory pressure data are collected in real time with a sampling time of 1 millisecond, and uploaded to the central control and information processing subsystem 3, and the central control and information processing subsystem 3 performs data processing and displays it on the display interface of the human-computer interaction subsystem 4, and the data is stored in the data storage device of the central control and information processing subsystem 3.

[0060] Step 3, the human-computer interaction subsystem 4 sends the stop evaluation instruction from the user to the central control and information processing subsystem 3, and the central control and information processing subsystem 3 transmits the instruction to the MCU microcontroller 2 through the serial port, and the MCU microcontroller 2 controls the patient interface subsystem to stop the evaluation workflow.

[0061] Step 4: Repeat the expiratory flow and inspiratory pressure information collection phase under normal breathing conditions. The data collection time is about 10 seconds. The entire evaluation process is completed.

Claims

1. A device for detecting pulmonary lobe ventilation function, characterized in that: Includes patient interface subsystem, central control and information processing subsystem, human-computer interaction subsystem, and power supply subsystem; The patient interface subsystem can block the patient's target bronchus to isolate the selected lung lobe, allowing the patient to inhale a fixed amount of 3 He and O2 mixed gas, and can collect the patient's airway inspiratory pressure, airway exhaled gas flow, exhaled gas CO2 and O2 component data, and send them to the central control and information processing subsystem; The central control and information processing subsystem is connected to the patient interface subsystem and the human-computer interaction subsystem, thereby being able to start / stop the detection of the ventilation function of the pulmonary lobe, receive the airway pressure flow of the isolated pulmonary lobe and the carbon dioxide and oxygen component information of the exhaled gas of the target pulmonary lobe, evaluate the ventilation status of the isolated pulmonary lobe and send it to the human-computer interaction subsystem for display; or, the gas concentration change at the bronchial orifice of the target pulmonary lobe can be directly evaluated through the negative pressure bypass system; The human-computer interaction subsystem is used for the operator to input / query patient information, send start / stop pulmonary lobe ventilation function detection instructions to the central control and information processing subsystem, and graphically display the evaluation information of the isolated pulmonary lobe; The power subsystem is connected to the mains power supply, and is also electrically connected to the patient interface subsystem, the central control and information processing subsystem, and the human-computer interaction subsystem, so as to provide working power.

2. A pulmonary lobe ventilation function detection device according to claim 1, characterized in that: The patient interface subsystem includes a main controller unit, a communication unit, a gas circuit control unit, a flow monitoring unit, a pressure detection unit, a breathing detection unit, a data storage unit, a CO2 detection unit and an O2 detection unit.

3. A pulmonary lobe ventilation function detection device according to claim 2, characterized in that: The main controller unit is connected to the communication unit, the air circuit control unit, the flow monitoring unit, the pressure detection unit, the data storage unit, and the breathing detection unit; it is capable of receiving the start / stop ventilation check instruction sent by the central control and information processing subsystem through the communication unit, controlling the air circuit control unit to close / open the respiratory / inspiratory airway, receiving real-time data from the flow detection unit and the pressure detection unit, storing them in the data storage unit, and uploading the real-time pressure and flow data to the central control and information processing subsystem through the communication unit.

4. A pulmonary lobe ventilation function detection device according to claim 3, characterized in that: The air path control unit includes an inhalation valve V1 and an exhalation valve V2; the inhalation valve V1 is used to close / open the inhalation passage, and the exhalation valve V2 is used to close / open the exhalation passage.

5. A pulmonary lobe ventilation function detection device according to claim 4, characterized in that: The central control and information processing subsystem is capable of sending instructions to the main controller unit, thereby controlling the patient interface subsystem to enter the expiratory flow and inspiratory pressure data collection phase of the selected lung lobe under normal breathing conditions; During the data collection stage, the breathing detection unit samples the flow sensor at a certain sampling time interval, filters the sampled data and stores it in the flow signal array, and obtains the flow curve by real-time fitting; when the slope of the fitted flow curve is greater than a certain threshold and the flow is greater than a certain preset value, it is determined that the patient has an inhalation or exhalation action.

6. A pulmonary lobe ventilation function detection device according to claim 5, characterized in that: When the patient is in the inhalation phase, the inhalation valve V1 opens, the exhalation valve V2 closes, and the gas inhaled by the patient enters the selected lung lobe from the inhalation port through the inhalation valve V1; When the patient is in the exhalation phase, the exhalation valve V2 opens and the inhalation valve V1 closes. The gas exhaled by the patient passes through the exhalation valve V2 and is input into the CO2 detection unit and O2 detection unit connected in series for gas component analysis. The analysis data is uploaded to the central control and information processing subsystem.

7. A pulmonary lobe ventilation function detection device according to claim 4, characterized in that: The central control and information processing subsystem can send instructions to the main controller unit, thereby controlling the patient interface subsystem to enter an evaluation working state, during which the inhalation valve V1 is closed; During the evaluation working state, the breathing detection unit samples the pressure sensor at a certain sampling time interval, filters the sampled data and stores it in the pressure signal array, and obtains the pressure curve by real-time fitting; When the slope of the pressure curve is greater than a certain threshold and the pressure is greater than a certain preset value, it is determined that the patient has an exhalation action; At the beginning of the exhalation phase, the breathing detection unit samples the flow sensor at a certain sampling time interval, filters the sampled data and stores it in the flow signal array, and obtains the flow curve by real-time fitting; When the slope of the flow curve is greater than a certain threshold and the flow rate is greater than a certain preset value, it is determined that the patient has an inhalation action.

8. A pulmonary lobe ventilation function detection device according to claim 7, characterized in that: When the patient is in the exhalation state, the exhalation valve V2 opens, and the gas exhaled by the patient is input into the CO2 detection unit and the O2 detection unit in series through the exhalation valve V2 for gas component analysis, and the analysis data is uploaded to the central control and information processing subsystem; the central control and information processing subsystem can realize continuous negative pressure bypass flow and continuously collect the gas concentration level of the target lung bronchial opening; When the patient is in the inhalation state, the exhalation valve V2 is closed to prevent external gas from entering the selected lung lobe.

9. A pulmonary lobe ventilation function detection device according to claim 7 or 8, characterized in that: The central control and information processing subsystem evaluates the ventilation status of the isolated lung lobe, including: if the O2 and CO2 concentrations in the exhaled air drop rapidly, it is determined that the selected lung lobe has bypass ventilation.

10. A device for detecting pulmonary lobe ventilation function according to claim 9, characterized in that: The central control and information processing subsystem is also used to establish and maintain a patient database to store the patient's isolated lung lobe assessment information.

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