Integrated device for cough induction based on air flow stimulation and real-time monitoring

Abstract

The application discloses a cough reflex evoking and real-time monitoring integrated device based on airflow stimulation and belongs to the technical field of medical instruments, which comprises a handheld shell, a mouthpiece and internal physical evoking, exhalation measurement and biological feedback modules, the physical evoking module outputs constant-temperature pulse airflow to evoke cough reflex at the end of inspiration according to the breathing phase monitored by a sensor, the exhalation flow measurement module acquires the peak flow rate value by using the pressure difference principle, the biological feedback module provides feedback through an indicator light and voice according to the flow rate value, and the device is integrated with a wireless communication unit and a memory. The application can realize safe and accurate evoking of cough reflex, replace manual assistance, realize objective quantification of the core index, namely, the peak flow rate, guide patients to actively adjust the breathing mode through a multi-modal feedback mechanism, effectively improve the positivity and safety of rehabilitation training, and realize digital management of nursing data.

Description

Technical Field

[0001] This invention belongs to the field of medical device technology, and in particular to an integrated device for inducing and real-time monitoring cough based on airflow stimulation. Background Technology

[0002] Coughing is a crucial protective reflex for the body to clear airway secretions and foreign objects. In clinical settings such as post-thoracic surgery, neurosurgery, and respiratory medicine, bedridden patients are often unable to perform an effective cough independently due to postoperative pain, muscle weakness, cognitive impairment, or nerve damage. This often leads to airway secretion retention, which in turn can cause serious pulmonary complications such as atelectasis, aspiration pneumonia, and respiratory failure.

[0003] Currently, in clinical nursing practice, nurses typically use a combination of verbal instructions and manual assistance to help patients clear sputum. This includes repeatedly teaching patients breathing techniques and manually pressing the abdomen or cricoid cartilage. However, this manual assistance method not only requires a high degree of patient understanding and cooperation, but pressing the cricoid cartilage also poses safety risks such as laryngeal distortion or airway obstruction. Furthermore, nurses need to be at the bedside for extended periods, resulting in high labor costs and highly inconsistent effectiveness. Existing mechanical sputum clearance devices, such as vibratory sputum clearance machines, can help loosen sputum, but they cannot induce an active cough reflex in patients, still requiring patient cooperation or subsequent suctioning. Moreover, these devices are usually bulky and expensive, making them unsuitable for routine bedside use.

[0004] Regarding cough induction and monitoring techniques, while existing technologies involve cough sensitivity and peak flow rate detection, they mostly employ chemical stimulation methods such as citric acid nebulization. This can easily cause patients to cough or experience airway spasm, and may even trigger asthma, posing a high risk of application for patients with sensitive airways post-surgery. Furthermore, existing electrical stimulation cough aids generally have low patient acceptance due to their invasiveness or operational complexity. Meanwhile, common respiratory training equipment often focuses on improving inspiratory muscle strength, lacking objective quantitative assessment of cough effectiveness and immediate biofeedback mechanisms, making it difficult for nurses to obtain scientific basis for judgment.

[0005] In summary, current technologies clearly lack a portable, intelligent device capable of safely and non-invasively inducing a patient's cough reflex and objectively quantifying peak expiratory flow rate to provide real-time positive feedback. This results in the inability to accurately assess patients' cough efficacy in clinical care, hindering patient compliance due to the lack of intuitive feedback, and making automated collection and management of related nursing data difficult. Therefore, developing a cough-assisted training device that integrates airflow physical stimulation induction, real-time flow rate monitoring, biofeedback, and data-driven management is of significant practical value for improving the safety, effectiveness, and digitalization of airway clearance care. Summary of the Invention

[0006] The purpose of this invention is to provide an integrated device for cough induction and real-time monitoring based on airflow stimulation, so as to solve the problems mentioned in the background art.

[0007] To achieve the above objectives, the present invention provides the following technical solution: an integrated device for real-time monitoring of cough induction and peak expiratory flow rate based on airflow stimulation includes a handheld housing, a detachable mouthpiece disposed at the front end of the handheld housing, and a physical induction module, an expiratory flow measurement module, and a biofeedback module disposed inside the handheld housing. The mouthpiece has a central airway that is bidirectionally usable for both inhalation and exhalation. An antibacterial filter is disposed at the connection between the mouthpiece and the handheld housing, the antibacterial filter being used to block pathogens from penetrating into the interior of the handheld housing during airflow exchange.

[0008] The physical induction module includes a miniature air pump, an air reservoir, a solenoid valve, an airflow sensor, and a controller. The outlet of the miniature air pump is connected to the inlet of the air reservoir via a pipeline. The air reservoir buffers and stabilizes the compressed airflow generated by the miniature air pump. The solenoid valve is located on the connecting pipeline between the air reservoir and the central airway. The airflow sensor is located in the central airway and electrically connected to the controller, used to detect the direction and velocity of the patient's inspiratory and expiratory airflow in real time. Based on the respiratory phase signal fed back by the airflow sensor, when the controller detects that the inspiratory airflow has dropped from its peak to a preset zero point at the end of inspiratory phase, it outputs an opening command to the solenoid valve, causing the solenoid valve to remain open for 0.3 to 0.8 seconds. This allows the pulsed airflow in the air reservoir to be ejected into the patient's pharynx through the central airway, generating a cough reflex through mechanical physical stimulation.

[0009] In a preferred embodiment of this scheme, the physical induction module further includes a heating and temperature control chamber and a temperature sensor disposed on the airflow path. The heating and temperature control chamber maintains the output pulse airflow at 34 to 37 degrees Celsius under the adjustment of the controller, thereby avoiding airway spasm caused by cold air stimulation. The surface of the handheld housing is provided with adjustment buttons, which are connected to the controller and are used to switch the output pressure of the micro air pump to multiple preset pressure levels.

[0010] In a preferred embodiment, the expiratory flow measurement module includes a throttling device disposed within the central airway. A first pressure tap and a second pressure tap are respectively constructed on both sides of the throttling device. A differential pressure sensor connected to the first and second pressure taps is disposed within the handheld housing. The differential pressure sensor is used to convert the pressure difference generated by the airflow passing through the throttling device into an electrical signal. The expiratory flow measurement module also includes a signal conditioning circuit. The signal conditioning circuit amplifies, filters, and performs analog-to-digital conversion on the electrical signal before transmitting it to the controller. The controller calculates the real-time expiratory flow according to a preset flow rate calibration formula and extracts the maximum instantaneous flow rate value during a single cough as the peak expiratory flow rate value.

[0011] In a preferred embodiment, the biofeedback module includes a visual feedback unit and an auditory feedback unit. The visual feedback unit includes a three-color indicator light and a display screen disposed on the surface of the handheld housing. The controller internally presets a first threshold of 160 liters per minute and a second threshold of 270 liters per minute. When the peak expiratory flow rate is less than the first threshold, the controller controls the three-color indicator light to display red to indicate an ineffective state; when the peak expiratory flow rate is between the first and second thresholds, it displays yellow to indicate a damaged cough state; when the peak expiratory flow rate is greater than or equal to the second threshold, it displays green to indicate an effective state. The auditory feedback unit includes a voice chip and a speaker. The controller triggers the voice chip to call the corresponding encouraging voice according to the range of the peak expiratory flow rate.

[0012] In a preferred embodiment of this design, the handheld housing also integrates a wireless communication unit and a memory. The controller records raw data, including training time, peak expiratory flow rate, number of coughs, and effectiveness, in the memory and transmits the raw data to a remote monitoring terminal in real time via the wireless communication unit. The surface of the handheld housing is also provided with an emergency stop button, which is connected to the power supply circuit of the solenoid valve via a physical circuit to cut off the power supply to the solenoid valve in an emergency.

[0013] Compared with the prior art, the technical effects and advantages of the present invention are as follows:

[0014] This integrated device for cough induction and real-time monitoring based on airflow stimulation precisely stimulates the pharynx at the end of inhalation using a physical constant-temperature pulsed airflow, achieving safe induction of the cough reflex and replacing the potentially unsafe manual pressure stimulation.

[0015] By integrating a differential pressure flow measurement structure, the core physiological indicator of peak expiratory flow rate during coughing can be objectively quantified. Combined with a multimodal biofeedback mechanism, patients can actively adjust their breathing patterns under visual and auditory guidance, enhancing their motivation for rehabilitation training. Simultaneously, the digital management unit enables automatic collection and remote transmission of nursing data, allowing nurses to monitor patients' airway clearance status without requiring constant bedside monitoring, significantly improving the efficiency and scientific rigor of clinical nursing. Attached Figure Description

[0016] To more clearly illustrate the specific embodiments of the present invention or the technical solutions in the prior art, the drawings used in the description of the specific embodiments or the prior art will be briefly introduced below. Obviously, the drawings described below are some embodiments of the present invention. For those skilled in the art, other drawings can be obtained from these drawings without creative effort.

[0017] Figure 1 This is a schematic diagram of the overall structure of the integrated device for real-time monitoring of cough induction and peak expiratory flow rate based on airflow stimulation according to an embodiment of the present invention.

[0018] Figure 2 This is a schematic diagram of the airway and sensor distribution according to an embodiment of the present invention;

[0019] Figure 3 This is an electrical control block diagram according to an embodiment of the present invention.

[0020] In the diagram: 1. Handheld housing; 2. Mouthpiece; 3. Antibacterial filter; 4. Miniature diaphragm air pump; 5. Air storage chamber; 6. Solenoid valve; 7. Airflow sensor; 8. Differential pressure flow sensor; 81. Throttling device; 82. First pressure tap; 83. Second pressure tap; 84. Differential pressure sensor; 9. Signal conditioning circuit; 10. Controller; 11. Wireless communication unit; 12. Memory; 13. Voice chip; 14. Speaker; 15. LED indicator; 16. Display screen; 17. Lithium battery; 18. Type-C charging interface; 19. Power switch; 20. Mode selection button; 21. Emergency stop button. Detailed Implementation

[0021] In the following description, numerous specific details are set forth in order to provide a more thorough understanding of the invention. However, it will be apparent to those skilled in the art that the invention can be practiced without one or more of these details. In other instances, certain technical features well-known in the art have not been described in order to avoid obscuring the invention.

[0022] Unless otherwise defined, the directions mentioned herein, such as up, down, left, right, front, back, inside, and outside, are based on the directions shown in the figures of this invention, and are explained here together.

[0023] This embodiment provides, for example Figures 1 to 3 The integrated device for real-time monitoring of cough induction and peak expiratory flow rate based on airflow stimulation shown includes a handheld housing 1, a detachable mouthpiece 2, an antibacterial filter 3, a miniature diaphragm air pump 4, an air storage chamber 5, a solenoid valve 6, an airflow sensor 7, a differential pressure flow sensor 8, a signal conditioning circuit 9, a controller 10, a wireless communication unit 11, a memory 12, a voice chip 13, a speaker 14, an LED indicator 15, a display screen 16, a lithium battery 17, a Type-C charging interface 18, a power switch 19, a mode selection button 20, and an emergency stop button 21.

[0024] In this embodiment, the handheld housing 1 serves as the main support structure of the entire device. Its interior is defined by brackets or slots, defining multiple installation spaces to accommodate electronic components and airway assemblies. The handheld housing 1 is ergonomically designed for easy one-handed use by medical personnel or patients. A mouthpiece 2 is threadedly or snap-fitted to the front end of the handheld housing 1. The mouthpiece 2 has a central airway that serves as a common passage for the patient's inhalation, receiving pulsed airflow stimulation, and coughing / exhalation. To ensure hygiene and safety during clinical use, an antibacterial filter 3 is installed at the physical interface between the mouthpiece 2 and the handheld housing 1. The antibacterial filter 3 contains high-efficiency air filter fibers that filter pathogenic microorganisms during bidirectional airflow, preventing respiratory secretions from entering the handheld housing 1 and causing cross-infection. It also protects the internal sensors from moisture and impurities.

[0025] In this embodiment, the core of the physical induction module lies in generating mechanical physical stimulation through controlled compressed airflow. Specifically, a miniature diaphragm air pump 4 is fixed to the bottom area of ​​the handheld housing 1. Its air inlet is connected to the outside atmosphere through a through hole on the housing, and its air outlet is connected to a hose leading to the air storage chamber 5. The miniature diaphragm air pump 4 works continuously under the drive of the controller 10, compressing the outside air and storing it in the air storage chamber 5. The air storage chamber 5 plays the role of air pressure buffering and stabilizing, ensuring that the stored airflow has constant pressure energy. The outlet end of the air storage chamber 5 is connected to the air inlet end of the solenoid valve 6 through a pipeline. The output end of the solenoid valve 6 is directly connected to the side wall of the central airway of the mouthpiece 2. The solenoid valve 6 adopts a high-speed response miniature electromagnetic switch and is controlled by the pulse width modulation signal output by the controller 10.

[0026] In this embodiment, in order to achieve precise control of the induction timing, the airflow sensor 7 is set at the central airway near the patient end. The airflow sensor 7 collects the static pressure changes and flow direction signals in the central airway in real time and transmits the collected analog signals to the controller 10. The controller 10 runs a respiratory phase recognition algorithm, which determines the patient's respiratory cycle by monitoring the positive and negative values ​​and slope changes of the airflow signal. When the controller 10 detects through the airflow sensor 7 that the patient is at the end of the inspiratory phase, that is, when the inspiratory flow rate drops rapidly from the peak and approaches the zero mark, the controller 10 immediately sends a driving voltage to the solenoid valve 6, causing the solenoid valve 6 to open instantly. At this time, the compressed airflow accumulated in the air storage chamber 5 is injected into the patient's oropharynx in the form of a pulse. The injection time of the pulse airflow is maintained between 0.3 seconds and 0.8 seconds. This sudden physical airflow will touch the cough receptors on the pharyngeal and airway mucosa, thereby inducing the body to produce an involuntary reflexive cough action.

[0027] In this embodiment, a heating and temperature control cavity and a temperature sensor are integrated along the airflow output path. The heating and temperature control cavity is wound with a flexible heating resistance wire. The controller 10 adjusts the heating power through pulse width modulation technology. The temperature sensor monitors the temperature of the airflow to be output to the patient in real time and sends the data back to the controller 10. The controller 10 uses a proportional-integral-derivative control algorithm to adjust and lock the airflow temperature within the range of 34 to 37 degrees Celsius. This constant temperature design avoids the reflex airway spasm or patient discomfort that may be caused by cold air directly entering the airway, further improving the safety and tolerability of the induction process.

[0028] In this embodiment, for adjusting the intensity of the induction, the mode selection button 20 on the surface of the handheld housing 1 is electrically connected to the controller 10. Medical staff can switch the operating power of the miniature diaphragm air pump 4 or the opening pressure difference of the solenoid valve 6 by operating the mode selection button 20. In this embodiment, there are three preset pressure levels: weak, medium, and strong, which correspond to the output pressure of five centimeters of water column, ten centimeters of water column, and fifteen centimeters of water column, respectively, to meet the actual needs of different groups such as postoperative weak patients, regular rehabilitation patients, and patients with low cough sensitivity.

[0029] In this embodiment, when the patient experiences a cough reflex due to airflow stimulation, the device enters the cough efficacy monitoring stage. The expiratory flow measurement module utilizes the pressure difference principle to achieve high-precision flow rate capture, such as... Figure 2As shown, a differential pressure flow sensor 8 is connected in series in the expiratory path of the central airway. The differential pressure flow sensor 8 includes a built-in throttling element 81, which can be a Venturi tube structure or an orifice plate structure. A first pressure tap 82 is provided on the upstream side of the throttling element 81, and a second pressure tap 83 is provided on the throat or downstream side of the throttling element 81. When the instantaneous high-pressure expiratory flow generated by coughing passes through the throttling element 81, a pressure difference conforming to Bernoulli's equation is generated between the first pressure tap 82 and the second pressure tap 83 due to the change in the flow cross-sectional area. The two pressure input terminals of the differential pressure sensor 84 are connected to the first pressure tap 82 and the second pressure tap 83 respectively through pressure guide tubes, converting the physical pressure difference signal into a weak voltage signal.

[0030] In this embodiment, the signal conditioning circuit 9 preprocesses the signal output by the differential pressure sensor 84. The signal conditioning circuit 9 integrates a high-input-impedance instrumentation amplifier to amplify the millivolt-level raw electrical signal to the range recognizable by the controller 10. It also uses a fourth-order low-pass filter to filter out electromagnetic noise generated by vibration or the operation of the air pump in the environment. The processed signal is then converted into a digital sequence by an analog-to-digital converter and finally transmitted to the controller 10. The controller 10 uses a calibrated mathematical formula—the linear mapping between peak expiratory flow rate and the square root of the pressure difference—to calculate the real-time instantaneous expiratory flow rate. The controller 10 uses a software algorithm to capture the maximum instantaneous flow point during a single cough, thereby obtaining the peak expiratory flow rate value. The measurement range of this module covers 0 to 600 liters per minute, fully covering all physiological indicators from weak to strong coughs, and the measurement accuracy is maintained within ±2%.

[0031] In this embodiment, the biofeedback module transforms measurement results into visible and audible information for the patient through a multi-dimensional interactive design. The handheld housing 1 has an LED indicator 15 and a display screen 16 on its surface. The controller 10 compares the measured peak expiratory flow rate with internally stored key thresholds. The first threshold is set at 160 liters per minute; a value below this usually indicates that coughing is ineffective in clearing secretions deep in the airway. The second threshold is set at 270 liters per minute, representing a clinically acceptable level of cough strength. If the calculated peak expiratory flow rate is less than 160 liters per minute, the controller 10 drives the LED indicator 15 to display red and shows an ineffective cough prompt on the display screen 16. If the peak expiratory flow rate is between 160 and 270 liters per minute, the LED indicator 15 switches to yellow, indicating impaired coughing but with some expectoration effect. If the peak expiratory flow rate is greater than or equal to 270 liters per minute, the LED indicator 15 displays green.

[0032] In this embodiment, the display screen 16 not only displays specific numerical values ​​but also provides feedback in the form of graphical animations. For example, it draws a graph of the liquid column height that fluctuates synchronously with the expiratory flow rate, allowing the patient to intuitively feel the results of their efforts. Furthermore, the auditory feedback unit, composed of the voice chip 13 and the speaker 14, works synchronously. The controller 10 retrieves corresponding encouraging audio through the voice chip 13 based on the measured flow rate level. For example, when a green effective zone is detected, the speaker 14 plays a "Great job, please keep it up" message; when a red zone is detected, it plays a guiding message, "Please exert more force during the induction." This audiovisual biofeedback mechanism significantly enhances the patient's enthusiasm for participating in rehabilitation training, transforming the patient from a passive participant in induced actions to an active mastery of skills.

[0033] In this embodiment, data management and communication functions provide support for digital clinical nursing. The wireless communication unit 11 inside the handheld housing 1 supports Bluetooth Low Energy protocol or wireless LAN protocol. After each training session, the controller 10 packages key parameters such as training time, gear setting, peak expiratory flow rate of multiple consecutive coughs, and induction success rate into an encrypted data packet. This data is stored in the local memory 12 as a backup, and also transmitted through the wireless communication unit 11 to the remote monitoring terminal at the nurse station or the mobile nursing PDA held by medical staff. The nurse station software performs trend analysis on the received historical data and generates a recovery curve for the patient's cough ability. If the system detects that a patient has not produced an effective cough greater than 160 liters per minute in three consecutive training sessions, the nurse station background will automatically trigger an early warning pop-up, reminding the responsible nurse to go to the bedside for manual intervention assessment to prevent the development of pulmonary complications caused by secretion retention.

[0034] In this embodiment, the power module ensures the portability and continuous operation capability of the device. The built-in lithium battery 17 provides energy support for the entire system. The bottom of the handheld housing 1 is equipped with a Type-C charging port 18, which supports fast charging by a universal power bank or charging adapter. The power switch 19 is used to turn the entire system on and off. Considering safety, an emergency stop button 21 is set in a conspicuous position on the handheld housing 1. The emergency stop button 21 is directly connected in series with the power supply circuit of the solenoid valve 6 and the miniature diaphragm air pump 4 through hardware contacts. In the event of accidental airway obstruction or extreme discomfort of the patient, pressing the emergency stop button 21 can immediately cut off the airway power source and forcibly close the solenoid valve 6 to ensure patient safety.

[0035] In this embodiment, taking a patient on the first day after thoracic surgery as an example, the patient was afraid to cough forcefully due to pain from the surgical incision, resulting in rales in the lungs. The nurse first turned on the power switch 19, and selected the medium intensity according to the patient's physical condition through the mode selection button 20. The nurse instructed the patient to bite down on the mouthpiece 2 and take deep breaths. At this time, the miniature diaphragm air pump 4 began to pressurize the air storage chamber 5 and heated the constant temperature chamber to maintain the internal airflow at 35 degrees Celsius. The airflow sensor 7 monitored the patient's respiratory waveform in real time. When the inspiratory waveform was detected to reach its peak and begin to descend to zero, the controller 10 accurately captured the end of inhalation and instantly opened the solenoid valve 6. A controlled warm pulse airflow was sprayed into the patient's pharynx through the central airway. This physical impact caused the patient to cough momentarily defensively.

[0036] Subsequently, under the induction effect, the patient coughed up high-velocity gas. The airflow passed through the throttling element 81 of the differential pressure flow sensor 8, generating a pressure difference. The signal conditioning circuit 9 collected this pressure difference signal and converted it to the controller 10. The controller 10 calculated the peak expiratory flow rate of this cough to be 220 liters per minute. Since this value was in the yellow warning range, the LED indicator 15 lit up yellow, and the voice chip 13 drove the speaker 14 to emit an encouraging sound of "Push harder, you can do it!" The display screen 16 showed the corresponding liquid column height. After seeing the feedback, the patient cooperated with abdominal muscle exertion in the next induction cycle, increasing the peak expiratory flow rate to 300 liters per minute. At this time, the LED indicator 15 turned green, and the system determined that it was an effective expectoration cough. All data was transmitted to the nurse station through the wireless communication unit 11. The nurse saw on the PDA that the patient's effective cough count for the day had reached the target, and no additional nebulization suction treatment was needed.

[0037] This embodiment presents an integrated device for cough induction and real-time monitoring of peak expiratory flow rate based on airflow stimulation. By deeply integrating physical induction, precise measurement, and multimodal biofeedback, it completely changes the traditional reliance on subjective experience in cough training. The physical induction module achieves non-invasive, safe, and efficient cough awakening through precise timing control, solving the rehabilitation problem for patients unable to cough voluntarily. The expiratory flow measurement module, combined with clinical threshold judgment, provides scientific quantitative indicators for sputum expectoration training. The digital management architecture effectively reduces the workload of medical staff and improves the level of intelligence in ward airway management. The device has a compact overall structure, low cost, and is easy to popularize, making it highly practical in clinical postoperative rehabilitation, neurological sputum expectoration care, and other fields.

[0038] In the description of this invention, the connections and signal flow between components have been optimized to ensure real-time response and system stability. For example, the controller 10 uses a high-performance microcontroller chip with a main frequency that supports high-frequency data sampling, ensuring complete capture of explosive physiological actions such as coughing. The volume of the air storage chamber 5 has been rigorously calculated to ensure sufficient energy for a single pulse without making the handheld housing 1 too bulky. This meticulous design logic permeates every detail of the device, aiming to provide patients with the best rehabilitation experience and medical institutions with a reliable auxiliary treatment method.

[0039] It should be noted that, in this document, relational terms such as "one" and "two" are used merely to distinguish one entity or operation from another, and do not necessarily require or imply any such actual relationship or order between these entities or operations. Furthermore, the terms "comprising," "including," or any other variations thereof are intended to cover non-exclusive inclusion, such that a process, method, article, or apparatus that comprises a list of elements includes not only those elements but also other elements not expressly listed, or elements inherent to such a process, method, article, or apparatus. Without further limitations, the phrase "comprising an element defined as..." does not exclude the presence of other identical elements in the process, method, article, or apparatus that includes said element.

[0040] Although embodiments of the invention have been shown and described, it will be understood by those skilled in the art that various changes, modifications, substitutions and alterations can be made to these embodiments without departing from the principles and spirit of the invention, the scope of which is defined by the appended claims and their equivalents.

Claims

1. An integrated device for cough induction and real-time monitoring based on airflow stimulation, characterized in that, It includes a handheld housing (1), a detachable mouthpiece (2) located at the front end of the handheld housing (1), an antibacterial filter (3), a physical induction module, an expiratory flow measurement module, and a controller (10). The mouthpiece (2) has a central airway inside, and the antibacterial filter (3) is located at the connection between the mouthpiece (2) and the handheld housing (1). The physical induction module includes a miniature diaphragm air pump (4), an air storage chamber (5), a solenoid valve (6), and an airflow sensor (7). The outlet of the miniature diaphragm air pump (4) is connected to the inlet of the air storage chamber (5). The solenoid valve (6) is installed on the connecting pipe between the air storage chamber (5) and the central airway. The airflow sensor (7) is installed in the central airway and is electrically connected to the controller (10). The controller (10) outputs an opening command to the solenoid valve (6) based on the respiratory phase signal collected by the airflow sensor (7) when it detects that the inspiratory flow rate drops from the peak to the preset zero point at the end of inspiratory flow, so that the pulse airflow in the air storage chamber (5) is ejected through the central airway. The expiratory flow measurement module includes a differential pressure flow sensor (8) installed in the central airway. The differential pressure flow sensor (8) is signal connected to the controller (10).

2. The integrated device for cough induction and real-time monitoring based on airflow stimulation according to claim 1, characterized in that: The controller (10) outputs the opening command and controls the solenoid valve (6) to remain open for 0.3 to 0.8 seconds.

3. The integrated device for cough induction and real-time monitoring based on airflow stimulation according to claim 1, characterized in that: The physical induction module also includes a heating constant temperature cavity and a temperature sensor set in the airflow path. The controller (10) adjusts the power of the heating constant temperature cavity according to the feedback signal of the temperature sensor to maintain the output pulse airflow at 34 degrees Celsius to 37 degrees Celsius.

4. The integrated device for cough induction and real-time monitoring based on airflow stimulation according to claim 1, characterized in that: The surface of the handheld housing (1) is provided with a mode selection button (20) connected to the controller (10). The controller (10) switches the output pressure of the micro diaphragm air pump (4) to five centimeters of water column, ten centimeters of water column or fifteen centimeters of water column according to the input command of the mode selection button (20).

5. The integrated device for cough induction and real-time monitoring based on airflow stimulation according to claim 1, characterized in that: The differential pressure flow sensor (8) includes a throttling element (81) disposed in the central airway. A first pressure tap (82) and a second pressure tap (83) are respectively constructed on both sides of the throttling element (81). A differential pressure sensor (84) is disposed in the handheld housing (1) and is respectively connected to the first pressure tap (82) and the second pressure tap (83).

6. The integrated device for cough induction and real-time monitoring based on airflow stimulation according to claim 5, characterized in that: The expiratory flow measurement module also includes a signal conditioning circuit (9), which is connected to the differential pressure sensor (84) and the controller (10). The signal conditioning circuit (9) is used to amplify, filter and perform analog-to-digital conversion on the electrical signal output by the differential pressure sensor (84).

7. The integrated device for cough induction and real-time monitoring based on airflow stimulation according to claim 1, characterized in that: The device also includes a biofeedback module, which includes an LED indicator (15) and a display screen (16) on the surface of the handheld housing (1). The controller (10) has a first threshold of 160 liters per minute and a second threshold of 270 liters per minute. The controller (10) controls the LED indicator (15) to switch between displaying red, yellow or green based on the comparison result between the measured peak expiratory flow rate and the first and second thresholds.

8. The integrated device for cough induction and real-time monitoring based on airflow stimulation according to claim 7, characterized in that: The biofeedback module also includes a voice chip (13) and a speaker (14). The controller (10) triggers the voice chip (13) to call the corresponding voice signal and play it through the speaker (14) according to the range of the peak expiratory flow rate value.

9. The integrated device for cough induction and real-time monitoring based on airflow stimulation according to claim 1, characterized in that: The handheld housing (1) also integrates a wireless communication unit (11) and a memory (12). The controller (10) records data including training time, peak expiratory flow rate, number of coughs and effectiveness in the memory (12) and transmits it to the remote monitoring terminal through the wireless communication unit (11).

10. The integrated device for cough induction and real-time monitoring based on airflow stimulation according to claim 1, characterized in that: The surface of the handheld housing (1) is also provided with an emergency stop button (21), which is connected in series in the power supply circuit of the solenoid valve (6) via a physical circuit to cut off the power supply of the solenoid valve (6).

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