Clinical lung function rehabilitation apparatus for respiratory medicine department

Abstract

The invention discloses a clinical lung function rehabilitation apparatus for respiratory medicine in the technical field of lung function rehabilitation, which comprises a shell, a bandage is fixedly connected to the shell, an air passage and an atomization cavity are formed in the shell, one side of the air passage is communicated with the atomization cavity, a respiratory resistance component is arranged in the air passage, and a dosing component is arranged in the atomization cavity. One end of the air channel is detachably communicated with a breathing tube, the tail end of the breathing tube is detachably connected with a mouthpiece, one side of the shell is fixedly connected with a display controller, the display controller is fixedly connected with a storage battery, and the breathing resistance assembly and the medicine feeding assembly are both in signal connection with the display controller. The respiratory resistance is accurately adjusted through the magnetic damping technology, the lung function rehabilitation device is miniaturized, the sputum excretion and drug administration functions are combined in respiratory rehabilitation training, the drug administration rate is intelligently controlled according to respiratory resistance changes, the optimal training resistance can be automatically matched based on current lung function data and rehabilitation stages of a patient, and the rehabilitation training efficiency is improved. The probability of respiratory muscle injury is reduced, and convenience and intelligence of lung function rehabilitation training are improved.

Description

Technical Field

[0001] This invention belongs to the field of pulmonary function rehabilitation technology, specifically a pulmonary function rehabilitation device for respiratory medicine. Background Technology

[0002] With the increasing incidence of respiratory diseases, chronic respiratory diseases such as chronic obstructive pulmonary disease (COPD), bronchial asthma, and pulmonary fibrosis have become major public health problems worldwide. These diseases are usually accompanied by a progressive decline in lung function, leading to respiratory muscle fatigue and reduced ventilation efficiency, which severely affects patients' quality of life and can even endanger their lives.

[0003] While traditional rehabilitation methods have played a role in controlling disease progression, they still have many limitations in improving patients' lung function and quality of life. On the one hand, although respiratory rehabilitation training has been proven effective, traditional training methods such as pursed-lip breathing and diaphragmatic breathing require high levels of patient compliance and active participation, and it is difficult to accurately quantify the intensity and effect of training. On the other hand, for patients with severe airway secretion retention, traditional expectoration methods such as back percussion and nebulized inhalation are limited in their efficiency in promoting sputum expectoration and cannot meet the clinical needs for comprehensive management of respiratory diseases, as shown in the three-ball trainer. In addition, traditional pulmonary rehabilitation devices are often large and difficult to transport, making it inconvenient for patients to conduct rehabilitation training in various environments, as shown in the patent with publication number CN119838102A.

[0004] Therefore, it is necessary to propose a respiratory medicine clinical pulmonary function rehabilitation device that can precisely adjust respiratory resistance, combine sputum expectoration and drug administration functions in respiratory rehabilitation training, intelligently control the drug administration rate according to changes in respiratory resistance, and automatically match the optimal training resistance based on the patient's current pulmonary function data and rehabilitation stage. Summary of the Invention

[0005] To address the aforementioned issues, the present invention aims to provide a pulmonary function rehabilitation device for respiratory medicine. This device precisely adjusts respiratory resistance using magnetic damping technology, and is miniaturized and integrated. It combines sputum expectoration and drug administration functions in respiratory rehabilitation training, intelligently controlling the drug administration rate based on changes in respiratory resistance. Furthermore, it can automatically match the optimal training resistance based on the patient's current pulmonary function data and rehabilitation stage, reducing the probability of respiratory muscle damage and improving the convenience and intelligence of pulmonary function rehabilitation training.

[0006] To achieve the above objectives, the technical solution of the present invention is as follows: A respiratory medicine clinical pulmonary function rehabilitation device includes a shell, a strap fixedly connected to the shell, an airway and a nebulization chamber inside the shell, one side of the airway communicating with the nebulization chamber, a breathing resistance component disposed within the airway, a drug delivery component disposed within the nebulization chamber, a breathing tube detachably connected to one end of the airway, a mouthpiece detachably connected to the end of the breathing tube, a display controller fixedly connected to one side of the shell, a battery fixedly connected to the display controller, and both the breathing resistance component and the drug delivery component being signal-connected to the display controller. The respiratory resistance component is used to apply resistance to the patient's breathing movements through magnetically controlled damping technology, and promotes the loosening and movement of sputum toward the main bronchus through pulsed airflow generation and chest resonance, in conjunction with the patient's cough reflex to expel it. A drug delivery component for controlling the release rate and particle diameter of the nebulized drug solution based on the patient's inspiratory resistance. The display controller is used to display and select current respiratory resistance and drug administration parameters, intelligently customize pulmonary function rehabilitation plans based on the monitored patient's actual respiratory function, and coordinate the execution of various components.

[0007] The basic principle of this approach is as follows: A respiratory resistance component uses magnetically controlled damping technology to apply resistance to the patient's breathing, simulating a certain load during respiration. This enhances the strength and endurance of the respiratory muscles, improving lung function. Simultaneously, the device utilizes pulsed airflow generation and chest cavity resonance to loosen sputum in the patient's airway and move it towards the main bronchus, facilitating the patient's cough reflex to expel the sputum and maintain airway patency. Furthermore, the drug delivery component is linked to the inspiratory resistance, precisely controlling the release rate and particle diameter of the nebulized medication based on the patient's inspiratory resistance. This ensures the medication enters the patient's respiratory tract at an appropriate particle size and velocity, improving drug deposition efficiency and thus enhancing efficacy, alleviating respiratory symptoms, and aiding in the recovery of lung function. The display controller serves as the control center of the entire system. On the one hand, it displays and allows selection of current respiratory resistance and drug delivery parameters, enabling patients and medical staff to intuitively understand the operating status of the equipment and the treatment process. On the other hand, based on the monitored data of the patient's actual respiratory function, it uses built-in intelligent algorithms and programs to tailor a personalized pulmonary function rehabilitation plan for the patient. It also coordinates and controls the respiratory resistance component and drug delivery component to execute the rehabilitation plan in an orderly manner, achieving precise and intelligent management of the patient's pulmonary function rehabilitation.

[0008] The beneficial effects of the basic program are: 1. By employing magnetically controlled damping technology, resistance can be precisely applied to breathing movements according to the patient's different rehabilitation stages and individual differences. This helps meet the patient's personalized training needs during the lung function recovery process, gradually enhances the strength and endurance of respiratory muscles, improves lung ventilation and respiratory efficiency, promotes effective recovery of lung function, and reduces the risk of respiratory muscle damage caused by inappropriate resistance.

[0009] 2. By utilizing the principles of pulsed airflow generation and chest cavity resonance, sputum is loosened within the airway and smoothly moved towards the main bronchus. Combined with the patient's cough reflex, this method can more effectively expel sputum from the body, solving the problem of limited efficiency of traditional sputum expectoration methods for patients with severe airway secretion retention. It can significantly reduce the risk of complications such as lung infection and further improve the overall rehabilitation effect.

[0010] 3. The display controller integrates multiple functions. It can display and select current respiratory resistance and medication parameters, allowing patients and medical staff to intuitively understand the equipment's operating status and treatment progress. Based on the monitored patient's actual respiratory function data, and utilizing built-in intelligent algorithms and programs, it can tailor a personalized pulmonary function rehabilitation plan for the patient and coordinate the control of various components to execute the plan in an orderly manner. This not only improves the scientific rigor and precision of rehabilitation training but also reduces the requirements for patient autonomy and compliance, making rehabilitation training more convenient and efficient.

[0011] 4. The equipment adopts a miniaturized and integrated design concept, making it compact, portable, and mobile. Patients can easily conduct rehabilitation training in various environments such as at home, hospital wards, and rehabilitation centers, without being restricted by location. This greatly improves the convenience and accessibility of pulmonary function rehabilitation training, which is conducive to patients adhering to long-term rehabilitation treatment and thus better improving their quality of life. It has significant clinical application value.

[0012] Furthermore, the display controller includes a monitoring module, a training and matching module, and an output module. The monitoring module is used to monitor the patient's respiratory pressure, flow rate, frequency, and blood oxygen data, as well as the temperature and humidity data inside the housing. The training matching module is used to match appropriate rehabilitation plans and identify sputum viscosity based on the patient data obtained from monitoring using an AI algorithm model; The output module is used to adjust the parameters of each component according to the matched rehabilitation plan, and to prompt the patient to correctly execute the rehabilitation plan through the display and voice functions of the display controller.

[0013] The beneficial effects of the basic solution are: 1. The monitoring module in the display controller can comprehensively monitor the patient's respiratory pressure, flow, frequency and blood oxygen data, as well as the temperature and humidity data inside the shell, thereby providing detailed and accurate physiological information for the subsequent rehabilitation plan, ensuring that the rehabilitation plan fits the patient's actual physical condition, and avoiding poor rehabilitation results or potential risks due to inaccurate information.

[0014] 2. The training and matching module uses AI algorithm models to accurately match the most suitable rehabilitation plan for patients based on rich patient data obtained from monitoring. It can also identify the key physiological indicator of sputum viscosity and then select pulse airflow parameters and vibration motor amplitude in a targeted manner, making rehabilitation training more targeted and effective, and meeting the personalized needs of different patients for rehabilitation programs at different stages of rehabilitation.

[0015] Furthermore, the breathing resistance assembly includes a bellows, with a magnetic sleeve fixedly fitted to the outside of the bellows. Both ends of the bellows are fixedly connected to both ends of the magnetic sleeve. Permanent magnets are symmetrically slidably fitted between the bellows and the magnetic sleeve. Corresponding permanent magnets have a repulsive force between them, so that the bellows is in a semi-expanded state inside the magnetic sleeve. Symmetrical stabilizing holes are opened in the middle of the magnetic sleeve. Stabilizing rods are fixedly connected to the middle of each permanent magnet. The stabilizing rods pass through the stabilizing holes and are slidably fitted with the stabilizing holes. An electromagnetic coil is wound around the outer wall of the magnetic sleeve. The magnetic sleeve is fixedly connected to the inner wall of the airway. The end of the bellows away from the breathing tube is connected to an inspiratory one-way valve and a pulse airflow tube. The end of the inspiratory one-way valve away from the breathing tube is connected to the outside. The electromagnetic coil is connected to the display controller signal.

[0016] The beneficial effects of the basic scheme are: 1. By connecting the electromagnetic coil with the display controller, the magnetic flux of the electromagnetic coil can be precisely adjusted according to the rehabilitation plan set in the display controller and the actual respiratory data of the patient monitored. This allows for sensitive control of the expansion and contraction of the bellows, enabling precise adjustment of the patient's respiratory resistance to meet the patient's real-time rehabilitation needs and avoid problems such as excessive fatigue of the respiratory muscles or poor training effect caused by improper resistance.

[0017] 2. The end of the bellows furthest from the breathing tube is connected to the inspiratory one-way valve and the pulse airflow tube. The inspiratory one-way valve connects to the outside, ensuring the orderly entry and exit of air. At the same time, in conjunction with the pulse airflow tube, it can generate appropriate pulse airflow according to the instructions of the display controller. Combined with the operation of the breathing resistance component, it more effectively promotes the loosening of sputum and its movement towards the main bronchus, enhances the sputum clearance assistance function of the device, and improves the patient's airway patency. The effect is more significant, especially for patients with a lot of sputum or thick sputum.

[0018] Furthermore, a conical nozzle is connected to one end of the pulse airflow tube, and an air pump is connected to the other end of the pulse airflow tube. The pulse airflow tube is connected to a bellows. A sampling tube and an exhalation tube are sequentially opened on the inner wall of the airway near the breathing tube. An exhalation one-way valve is connected to the end of the exhalation tube. The air pump is connected to the display controller.

[0019] The beneficial effects of the basic design are: 1. A sampling tube and an expiratory tube are sequentially located on the inner wall of the airway near the breathing tube. The sampling tube can collect gas samples from the patient's airway in real time, providing the monitoring module with more multidimensional respiratory data, such as gas composition and flow rate changes. The expiratory tube is specifically designed to guide the patient's exhaled gas to the expiratory one-way valve for discharge, avoiding backflow and interference of exhaled gas in the airway, ensuring the accuracy and reliability of the monitoring data, and providing more comprehensive and accurate data support for the display controller to formulate personalized rehabilitation plans.

[0020] 2. The pulse airflow tube is tilted at 30° and connects to the corrugated tube. This ingenious angle design helps optimize the flow direction and distribution of airflow within the airway, allowing the pulse airflow to blend more smoothly with the patient's natural breathing airflow, reducing turbulence and resistance loss within the tube. Simultaneously, this angle ensures that the pulse airflow accurately targets the desired area, enhancing the flushing and propulsion effect on sputum, strengthening the sputum clearance assistance function of the rehabilitation device, and improving the overall rehabilitation outcome.

[0021] Furthermore, several vibration grooves are opened on the side walls of the housing, and a vibration motor is installed in each vibration groove. The output shaft of the vibration motor is opposite to that of the display controller. An eccentric block is fixedly connected to the output shaft of each vibration motor, and the vibration motor is connected to the display controller for signal connection.

[0022] The beneficial effects of the basic design are as follows: Vibration grooves and vibration motors are located on the sidewalls near the four corners of the casing. This four-corner distribution design allows vibration to be transmitted more evenly to all areas inside the casing, forming a comprehensive vibration field. When the vibration motor operates, the eccentric block fixed on its output shaft generates centrifugal force, causing the casing to vibrate in multiple dimensions. This vibration can be transmitted to the airway, enhancing the physical stimulation of the patient's airway walls and further loosening sputum. Combined with the respiratory resistance components and pulsed airflow, this multi-point synergistic effect promotes the movement of sputum towards the main bronchus, significantly improving sputum expectoration efficiency. This is especially beneficial for patients with thick and widely distributed sputum, better assisting in expectoration and reducing the risk of lung infection.

[0023] Furthermore, the drug delivery assembly includes an atomizing support, an atomizing mesh fixedly connected to the atomizing support, the atomizing support being fixedly connected to the side wall of the atomizing chamber, a shock-absorbing strip slidingly fitted inside the atomizing support, a shock-absorbing rack fixedly connected to one end of the shock-absorbing strip near the bellows, a stabilizing rack fixedly connected to the end of the stabilizing rod near the atomizing chamber, and a reversing gear provided inside the housing, with both the shock-absorbing rack and the stabilizing rack meshing with the reversing gear; A drug chamber is detachably installed inside the nebulization chamber. One end of the drug chamber has a drug delivery port, and a silicone valve is installed inside the drug delivery port. A liquid pump is installed on the inner wall of the nebulization chamber. The input end of the liquid pump is slidably engaged with the silicone valve, and the output end of the liquid pump is connected to a nozzle facing the nebulization mesh. Both the nebulization mesh and the liquid pump are connected to the display controller signal.

[0024] The beneficial effects of the basic design are: 1. The nebulizer mesh has excellent atomization performance, efficiently converting the liquid medication into tiny particles, ensuring that the medication enters the patient's respiratory tract at an appropriate particle size and velocity. The inlet of the liquid pump slides into a silicone valve, and the outlet connects to the nozzle and faces the nebulizer mesh. This design allows the liquid pump to precisely control the delivery volume and timing of the liquid medication. Based on the patient's inspiratory resistance and respiratory status, it accurately releases the nebulized medication during inhalation, improving drug deposition efficiency, enhancing therapeutic effects, and reducing drug waste and side effects.

[0025] 2. The sliding damping strips and connected damping racks inside the nebulizer support, in clever cooperation with the stabilizing rack and reversing gear, can effectively buffer the amplitude of the nebulizer mesh on the nebulizer support. Thus, the nebulization rate of the nebulizer mesh can be adjusted by the displacement of the stabilizing rod. Combined with the control of the liquid pump by the display controller, the dosage, administration rate and particle size can be changed according to the resistance of the breathing resistance component.

[0026] Furthermore, a liquid level sensor is installed inside the drug chamber. A conductive diaphragm slides between the outer periphery of the liquid pump and the inner wall of the nebulization chamber. Conductive switches are embedded in the inner walls of the nebulization chamber on both sides of the conductive diaphragm. A return spring is fixedly connected to one side of the conductive diaphragm and is fixedly connected to the inner wall of the nebulization chamber. When the patient inhales and a negative pressure is formed in the airway, the conductive diaphragm moves the return spring to connect the power supply to the liquid pump and the nebulization mesh to nebulize the liquid. When the patient exhales, the return spring pulls the conductive diaphragm to reset and cut off the power supply. The liquid level sensor is connected to the display controller signal.

[0027] The beneficial effects of the basic solution are: 1. The liquid level sensor installed in the medication chamber can monitor the remaining amount of medication in the chamber in real time and transmit the data signal to the display controller. This avoids treatment interruptions due to insufficient medication, ensures the continuity and effectiveness of rehabilitation training, improves the reliability of treatment and patient compliance. When the medication is insufficient, the display controller can promptly remind the user to replenish the medication, and even pause the medication administration operation when necessary, avoiding problems such as inaccurate medication administration or equipment idling due to insufficient medication.

[0028] 2. When the patient inhales, a negative pressure is created in the airway. Under the influence of the pressure change, the conductive diaphragm moves towards the liquid pump and triggers the conductive switch, thereby activating the liquid pump and the nebulizer mesh, achieving precise spraying and atomization of the medication. This design requires no additional mechanical or electronic triggering components, relying entirely on the patient's natural inhalation. It achieves a high degree of synchronization between the timing of drug administration and the patient's breathing rhythm, improving the accuracy and effectiveness of drug administration and reducing drug waste.

[0029] Furthermore, a saliva-proof filter membrane is laid at the connection between the mouthpiece and the breathing tube, and both ends of the breathing tube are connected to rotating buckles, which are used for detachable connection of the breathing tube to the airway and the mouthpiece.

[0030] The beneficial effects of the basic solution are: 1. Laying a saliva-proof filter membrane at the connection between the mouthpiece and the breathing tube can effectively prevent the patient's saliva from entering the breathing tube and the inside of the equipment, avoiding contamination of the equipment by bacteria, viruses and other microorganisms in the saliva, and reducing the risk of equipment failure.

[0031] 2. The mouthpiece is available in a variety of sizes to fit patients based on their age, mouth size, and individual differences. This ensures that patients of different ages (such as children, adults, and the elderly) and with different oral conditions can use the rehabilitation device correctly and comfortably, improving the device's versatility and accessibility, meeting the diverse clinical needs of respiratory medicine, and enabling more patients to benefit from this pulmonary function rehabilitation device.

[0032] Furthermore, the monitoring module includes a Hall sensor, a pressure sensor, a flow sensor, a blood oxygen sensor, and a temperature and humidity sensor. The Hall sensor is fixedly connected to the magnetic sleeve, the pressure sensor is fixedly connected to the inner wall of the airway, the flow sensor is connected to the end of the sampling tube, the blood oxygen sensor is fixedly connected to the outer edge of the mouthpiece, and the temperature and humidity sensor is fixedly connected to the display controller.

[0033] The basic approach offers several advantages: the monitoring module acquires a comprehensive range of data reflecting the patient's respiratory function. Based on this data, and combined with an AI algorithm model, the display controller accurately assesses the patient's lung function and rehabilitation stage. This allows for more precise adjustments to the rehabilitation plan, dynamically matching the most suitable parameters such as respiratory resistance, medication dosage, and frequency according to the patient's actual recovery, thereby improving the relevance and effectiveness of rehabilitation training.

[0034] Furthermore, the training matching module includes a sputum recognition model and a training decision tree model. A sputum recognition model is used to analyze sputum viscosity based on respiratory pressure waveform images using an LSTM neural network, and to select pulse airflow parameters and vibration motor amplitude. The training decision tree model is used to determine the patient's rehabilitation stage and lung function based on the monitored patient respiratory data, and to match the appropriate training intensity for this stage.

[0035] The beneficial effects of the basic solution are: 1. The sputum recognition model, based on an advanced LSTM neural network, can accurately determine the viscosity of sputum through in-depth analysis of respiratory pressure waveform images. This is a prerequisite for achieving precise sputum expectoration treatment, because sputum of different viscosities requires different pulse airflow parameters and vibration motor amplitudes to effectively loosen and expel it.

[0036] 2. The training decision tree model can accurately determine a patient's rehabilitation stage and current lung function status based on monitored respiratory data, such as respiratory pressure, flow rate, and frequency. Based on these findings, the model can match the patient with the most suitable training intensity for their current stage. This personalized rehabilitation plan ensures that the patient is not harmed by excessive training intensity, nor that insufficient training intensity negatively impacts rehabilitation outcomes.

[0037] 3. By combining a sputum recognition model with a training decision tree model, comprehensive management of patient sputum expectoration and rehabilitation training is achieved. These two models work together, enabling the device to simultaneously optimize sputum expectoration and breathing training parameters based on the patient's real-time physiological state. This intelligent management approach not only improves rehabilitation efficiency but also reduces intervention by medical staff, allowing patients to perform rehabilitation training more autonomously. Attached Figure Description

[0038] Figure 1 This is an isometric view of a respiratory medicine clinical pulmonary function rehabilitation device in an embodiment of the present invention.

[0039] Figure 2 This is a top view of the respiratory medicine clinical pulmonary function rehabilitation device in an embodiment of the present invention.

[0040] Figure 3 This is a top sectional view of the respiratory medicine clinical pulmonary function rehabilitation device in an embodiment of the present invention.

[0041] Figure 4 This is a side sectional view of the respiratory medicine clinical pulmonary function rehabilitation device in an embodiment of the present invention.

[0042] Figure 5 for Figure 3 A magnified view of part A in the middle.

[0043] Figure 6 for Figure 3 A magnified view of part B in the middle.

[0044] Figure 7 for Figure 1 The diagram shows the system framework of the controller.

[0045] The reference numerals in the accompanying drawings of this instruction manual include: 1. Housing; 2. Battery; 3. Display controller; 4. Breathing tube; 5. Mouthpiece; 6. Medication chamber; 7. Strap; 8. Nebulizer chamber; 9. Stabilizing rack; 10. Pulsating airflow tube; 11. Vibration groove; 12. Vibration motor; 13. Eccentric block; 14. Air pump; 15. Exhalation one-way valve; 16. Sampling tube; 17. Flow sensor; 18. Pressure sensor; 19. Airway; 20. Rotary buckle; 21. Magnetic sleeve; 22. Nebulizer support; 23. Nebulizer mesh; 24. Blood oxygen sensor; 25. Anti-saliva filter membrane; 26. Liquid level sensor; 27. Silicone valve; 28. Liquid pump; 29. ​​Reversing gear; 30. Shock-absorbing rack; 31. Nozzle; 32. Permanent magnet; 33. Inhalation one-way valve; 34. Conical nozzle; 35. Electromagnetic coil; 36. Waveform tube. Detailed Implementation

[0046] The following detailed description illustrates the specific implementation method: Example 1

[0047] The basics are as follows: Figures 1 to 6 As shown: A respiratory medicine clinical pulmonary function rehabilitation device includes a shell 1, with a strap 7 fixedly connected to the shell 1. An airway 19 and a nebulization chamber 8 are opened inside the shell 1. One side of the airway 19 is connected to the nebulization chamber 8. A breathing resistance component is installed in the airway 19, and a drug delivery component is installed in the nebulization chamber 8. A breathing tube 4 is detachably connected to one end of the airway 19, and a mouthpiece 5 is detachably connected to the end of the breathing tube 4. A display controller 3 is glued to one side of the shell 1, and a battery 2 is welded to the display controller 3. Both the breathing resistance component and the drug delivery component are signal connected to the display controller 3.

[0048] The respiratory resistance assembly is used to apply resistance to the patient's breathing movements through magnetically controlled damping technology. It promotes the loosening and movement of sputum towards the main bronchus through pulsed airflow generation and thoracic resonance, facilitating the patient's cough reflex. The assembly includes a bellows, with a magnetic sleeve 21 fixedly fitted to the outside of the bellows. Both ends of the bellows are bonded to the ends of the magnetic sleeve 21. Permanent magnets 32 are symmetrically slidably fitted between the bellows and the magnetic sleeve 21, and the corresponding permanent magnets 32 exert a repulsive force, causing the bellows to move within the magnetic sleeves. In a semi-relaxed state, the magnetic sleeve 21 has symmetrical stabilizing holes in the middle, and the permanent magnets 32 are all welded with stabilizing rods in the middle. The stabilizing rods pass through the stabilizing holes and slide with the stabilizing holes. The outer wall of the magnetic sleeve 21 is wound with an electromagnetic coil 35. The magnetic sleeve 21 is welded to the inner wall of the airway 19. The end of the bellows away from the breathing tube 4 is connected to the inhalation one-way valve 33 and the pulse airflow tube 10. The end of the inhalation one-way valve 33 away from the breathing tube 4 is connected to the outside. The electromagnetic coil 35 is connected to the display controller 3.

[0049] One end of the pulse airflow tube 10 is connected to a conical nozzle 34, and the other end of the pulse airflow tube 10 is connected to an air pump 14. The pulse airflow tube 10 is inclined at a 30° angle to the corrugated tube wall and is connected to the corrugated tube. A sampling tube 16 and an exhalation tube are sequentially opened on the inner wall of the airway 19 near the breathing tube 4. The end of the exhalation tube is connected to an exhalation one-way valve 15. The air pump 14 is connected to the display controller 3.

[0050] The side wall of the housing 1 has several vibration grooves 11, and each vibration groove 11 is equipped with a vibration motor 12. The output shaft of the vibration motor 12 is opposite to that of the display controller 3. An eccentric block 13 is eccentrically welded on the output shaft of each vibration motor 12. The vibration motor 12 is connected to the display controller 3 via signal.

[0051] The drug delivery assembly is used to control the release rate and particle diameter of the atomized drug solution based on the patient's inspiratory resistance. The assembly includes an atomizing support 22, on which an atomizing mesh 23 is welded. The atomizing support 22 is welded to the side wall of the atomizing chamber 8. A shock-absorbing strip slides within the atomizing support 22. A shock-absorbing rack 30 is welded to the end of the shock-absorbing strip near the bellows. A stabilizing rack 9 is welded to the end of the stabilizing rod near the atomizing chamber 8. A reversing gear 29 and a shock-absorbing rack are installed inside the housing 1. Both the 30 and the stabilizing rack 9 mesh with the reversing gear 29. A drug chamber 6 is detachably installed inside the atomizing chamber 8. One end of the drug chamber 6 has a drug delivery port, and a silicone valve 27 is installed inside the drug delivery port. A liquid pump 28 is bonded to the inner wall of the atomizing chamber 8. The input end of the liquid pump 28 is slidably engaged with the silicone valve 27. The output end of the liquid pump 28 is connected to a nozzle 31, which faces the atomizing mesh 23. The atomizing mesh 23 is made of piezoelectric ceramic material. Both the atomizing mesh 23 and the liquid pump 28 are connected to the display controller 3.

[0052] A liquid level sensor 26 is installed inside the drug chamber 6. A conductive diaphragm is slidably fitted between the outer periphery of the liquid pump 28 and the inner wall of the nebulization chamber 8. Conductive switches are embedded in the inner walls of the nebulization chamber 8 on both sides of the conductive diaphragm. A reset spring is adhered to one side of the conductive diaphragm and is fixedly connected to the inner wall of the nebulization chamber 8. When the patient inhales and a negative pressure is formed in the airway, the conductive diaphragm moves the reset spring to connect the power supply to the liquid pump 28 and the nebulization mesh 23 to nebulize the drug. When the patient exhales, the reset spring pulls the conductive diaphragm to reset and cut off the power supply. The liquid level sensor 26 is connected to the display controller 3.

[0053] Display controller 3 is used to display and select current respiratory resistance and drug administration parameters, intelligently customize pulmonary function rehabilitation plans based on the actual respiratory function of the monitored patient, and coordinate the execution of various components.

[0054] The mouthpiece 5 is made of medical silicone material, and a saliva-proof filter membrane 25 is laid at the connection with the breathing tube 4. The mouthpiece 5 is available in several sizes to fit the oral cavity size of patients of different ages. Both ends of the breathing tube 4 are connected to rotating buckles 20, which are used for the detachable connection of the breathing tube 4 with the airway 19 and the mouthpiece 5.

[0055] The specific implementation process is as follows: Existing clinical pulmonary function rehabilitation devices are generally large in size, making it inconvenient for patients to move them to different environments for use. Furthermore, although existing pulmonary function rehabilitation devices can integrate functions such as sputum expectoration, drug administration, and respiratory exercises, they cannot combine learning model algorithms to automatically determine the patient's rehabilitation stage and select an appropriate training plan based on the patient's respiratory data. This undoubtedly reduces the compliance of pulmonary function rehabilitation devices and is not conducive to the repetition and promotion of rehabilitation training.

[0056] When a patient uses the respiratory medicine clinical pulmonary function rehabilitation device of the present invention, the device is first secured to the chest using the straps 7 on the housing 1, with the display controller 3 facing outwards and the output shaft of the vibration motor 12 pointing towards the chest. A medical silicone mouthpiece 5, adapted to the size of the patient's mouth, is then connected to the breathing tube 4 via a rotating buckle 20. When the mouthpiece 5 is engaged, the anti-saliva filter membrane 25 prevents saliva from entering the device. After the display controller 3 is activated, the battery 2 powers the entire system, and the monitoring module immediately begins operation. Figure 1 and Figure 2 As shown.

[0057] When the patient performs breathing training, the breathing resistance component activates. The electromagnetic coil 35 generates a magnetic field under the command of the display controller 3. Gas pushes the permanent magnet 32 ​​between the bellows and the magnetic sleeve 21 to slide, changing the cross-sectional area of ​​the bellows and thus applying resistance to the airflow during the patient's breathing. Simultaneously, the air pump 14 delivers airflow to the pulse airflow tube 10 through the conical nozzle 34. The inclined pulse airflow tube 10 injects airflow into the bellows at a specific angle. Combined with the opening and closing of the inspiratory one-way valve 33, this forms a pulse airflow impacting the airway 19 and the patient's lungs and trachea. The vibration caused by the pulse airflow promotes the loosening of sputum. The vibration motors 12 at the four corners of the housing 1 drive the eccentric blocks 13 to rotate, generating multi-dimensional vibrations. After being buffered by the shock-absorbing pads, these vibrations are transmitted to the chest cavity, working in conjunction with the pulse airflow to move sputum towards the main bronchus, ultimately expelling it through the cough reflex. Figure 3 As shown.

[0058] When the patient inhales, the negative pressure in the airway 19 pushes the conductive diaphragm to stretch, the return spring rises, triggering the conductive switch. The liquid pump 28 draws a measured amount of medication from the silicone valve 27 in the medication chamber 6 and sprays it onto the nebulizer mesh 23 through the nozzle 31. The piezoelectric ceramic nebulizer mesh 23 vibrates at high frequency under the action of an electrical signal, atomizing the medication into tiny particles. At this time, the displacement of the permanent magnet 32 ​​drives the stabilizing rod to move. Through the transmission of the stabilizing rack 9, the reversing gear 29, and the damping rack 30, the length of the damping strip remaining in the nebulizer support 22 is adjusted. The change in the mass of the nebulizer support 22 affects the amplitude of the nebulizer mesh 23, thereby controlling the release rate of the nebulized medication, so that the medication accurately enters the respiratory tract with inhalation, such as... Figure 6 As shown.

[0059] For example, the display controller 3 controls the liquid pump 28 to vary the single-dose dosage between 0.1-1 ml. When the respiratory resistance is low, the nebulizer mesh 23 nebulizes the medication normally. At this time, the vibration frequency of the nebulizer mesh 23 is low and the amplitude is high, and the medication is quickly nebulized into large particles, which are carried into the patient's lungs by the faster respiratory airflow. When the respiratory resistance is high, the display controller 3 controls the liquid pump 28 to reduce the single-dose dosage. As the permanent magnets 32 move closer together, the stabilizing rod is displaced, and the steering gear pushes the damping strip into the nebulizer support 22, thereby reducing the amplitude of the high-frequency vibrating nebulizer mesh 23. At this time, the nebulization rate of the nebulizer mesh 23 decreases, but it can still slowly produce small particles of medication through high-frequency vibration. These particles are carried into the depths of the patient's trachea by the weaker respiratory airflow, achieving a better deposition effect. Figure 4 and Figure 5 As shown.

[0060] The display controller 3, acting as the core hub, receives data from the monitoring module in real time. It analyzes the respiratory pressure waveform using a sputum recognition model to determine sputum viscosity, and then adjusts the pulse airflow parameters and the amplitude of the vibration motor 12 accordingly. The training decision tree model assesses the rehabilitation stage based on respiratory data, automatically matches the training intensity, and guides the patient through the output module via a display interface and voice prompts. When the medication in the medication compartment 6 is low, the level sensor 26 sends a signal to the display controller 3 to remind the patient to replenish the medication. After training, the breathing tube 4 and mouthpiece 5 can be removed by rotating the buckle 20 for cleaning, ensuring the equipment's hygiene.

[0061] Example 2

[0062] The difference from the above embodiments is that, in conjunction with the appendix... Figure 7 As shown: The display controller 3 includes a monitoring module, a training and matching module, and an output module.

[0063] The monitoring module is used to monitor the patient's respiratory pressure, flow rate, frequency, and blood oxygen data, and to monitor the temperature and humidity data inside the housing 1. The monitoring module includes a Hall sensor, a pressure sensor 18, a flow sensor 17, a blood oxygen sensor 24, and a temperature and humidity sensor. The Hall sensor is fixedly connected to the magnetic sleeve 21, the pressure sensor 18 is fixedly connected to the inner wall of the airway 19, the flow sensor 17 is connected to the end of the sampling tube 16, the blood oxygen sensor 24 is fixedly connected to the outer edge of the mouthpiece 5, and the temperature and humidity sensor is fixedly connected to the display controller 3.

[0064] The training and matching module uses an AI algorithm model to match appropriate rehabilitation plans based on monitored patient data and to identify sputum viscosity. The training and matching module includes a sputum recognition model and a training decision tree model. The sputum recognition model is used to analyze sputum viscosity through respiratory pressure waveform images based on an LSTM neural network, and to select pulse airflow parameters and vibration motor amplitude. The training decision tree model is used to determine the patient's rehabilitation stage and lung function based on monitored patient respiratory data, and to match a training intensity suitable for this stage.

[0065] The output module is used to adjust the parameters of each component according to the matched rehabilitation plan, and to prompt the patient to correctly execute the rehabilitation plan through the display and voice functions of the display controller 3.

[0066] The specific implementation process is as follows: the Hall sensor senses the change in the magnetic field near the magnetic sleeve 21, the pressure sensor 18 monitors the breathing pressure in the airway 19, the flow sensor 17 obtains breathing airflow data through the sampling tube 16, the blood oxygen sensor 24 is attached to the edge of the lips to detect the blood oxygen concentration, and the temperature and humidity sensor provides real-time feedback on the internal environmental parameters of the shell 1.

[0067] After receiving the respiratory data collected by the monitoring module and generating a respiratory pressure waveform, the training matching module first preprocesses the waveform and extracts time-frequency features through wavelet transform:

[0068] Construct the feature matrix:

[0069] Calculation via LSTM gating:

[0070] The output yields a sputum viscosity score:

[0071] A sputum score less than 3 indicates thin sputum, while a sputum score greater than 6 indicates thick sputum.

[0072] The training of the decision tree model starts with the breathing vector features and determines the training intensity based on the splitting rule, while minimizing the Gini impurity:

[0073]

[0074] Thus, the training intensity decision rule is obtained:

[0075] After obtaining the sputum viscosity score and training intensity decision results based on the above calculation formula, the display controller 3 adjusts the sputum expectoration parameters: vibration frequency of vibration motor 12, pulse intensity of pulsed airflow; adjusts the respiratory resistance: magnetic field strength of electromagnetic coil 35; adjusts the single dose and nebulized particle size of nebulized drug delivery, thereby obtaining the most suitable rehabilitation training for the patient's current state, improving training and sputum expectoration efficiency, reducing respiratory muscle fatigue during training, and improving the patient's comprehensive pulmonary function rehabilitation index.

[0076] Specific experimental procedure: Experiment to verify the performance of lung function rehabilitation I. Experimental Objective The performance of this invention in terms of sputum expectoration efficiency, improvement of respiratory muscle fatigue, and comprehensive rehabilitation index was verified and compared with traditional methods.

[0077] II. Experimental Grouping Experimental group: 64 samples used the intelligent mode training of the lung function rehabilitation device of this invention for 4 weeks; Control group 1: 63 samples used the traditional three-ball breathing trainer + manual back percussion and sputum clearance training for 4 weeks; Control group 2: 30 samples received routine nebulized inhalation treatment for 4 weeks.

[0078] III. Sample Inclusion and Exclusion Criteria Inclusion criteria: patients diagnosed with moderate to severe COPD (GOLD grade II-III); 24-hour sputum volume >30ml; age 40-75 years, conscious and able to cooperate with training.

[0079] Exclusion criteria: serious cardiovascular disease; recent history of thoracic surgery; cognitive impairment.

[0080] IV. Experimental Methods All subjects received training twice daily, with an interval of ≥4 hours. Each training session consisted of three phases: 10 minutes of breathing resistance training, 5 minutes of expectoration therapy, and 5 minutes of nebulized drug administration. Training was conducted 5 days a week for 4 weeks.

[0081] Control group 1 received fixed 20 cm H2O resistance training and manual tapping at a frequency of 2 Hz and a force of 3 kg. Control group 2 received fixed 5 μm particle size and 0.5 ml dose nebulization.

[0082] V. Measurement Indicators Regarding the expectoration effect, the total amount of sputum in 24 hours (including nighttime sputum) was accurately measured by the standard sputum cup weighing method. The volume clearance rate of bronchial tree sputum was calculated by three-dimensional reconstruction using thin-slice CT scan of the lungs (1 mm slice thickness). The accuracy of the LSTM model in identifying sputum viscosity was verified by centrifugation sedimentation as the gold standard.

[0083] To improve respiratory function, weekly changes in FEV1 as a percentage of predicted value were measured using a pulmonary function instrument compliant with ATS standards. The increase in walking distance over 6 minutes was recorded using a 30-meter standardized corridor test. At the same time, the increase in resting SpO2 was recorded using a continuous pulse oximeter.

[0084] In the assessment of respiratory muscle fatigue, the maximum inspiratory pressure (MIP) in the oral cavity is monitored in real time. When the MIP decreases by more than 20% from the baseline and lasts for 5 minutes, it is defined as a fatigue event. At the same time, the Borg scale (0-10 points) is used to allow patients to self-report the degree of dyspnea after training.

[0085] For the performance of the intelligent system, the consistency ratio between the training intensity automatically matched by the device and the independent assessment results of clinicians was recorded. The lung drug deposition rate was calculated by SPECT imaging technology (technetium-99m labeled nebulized drugs). The training plan completion rate was statistically analyzed as a compliance indicator, and patient satisfaction visual analog scale scores (0-10 points) were collected.

[0086] VI. Experimental Results The results are shown in the table below: Table 1. Comparison of key efficacy indicators index Experimental group (n=64) Control group 1 (n=63) Control group 2 (n=30) p-value Changes in sputum volume over 24 hours (ml) +18.6±3.2* +5.4±2.1 +8.3±2.5 ＜0.001 Sputum clearance rate (%) 72.3±6.5* 48.7±7.2 52.1±6.8 ＜0.001 FEV1 improvement (%) +12.5±3.1* +3.2±1.8 +4.7±2.0 ＜0.001 6MWD increase (m) +80±22* +25±15 +32±18 ＜0.001 <![CDATA[SpO2 improvement (%)]]> +4.3±1.1* +1.2±0.7 +1.8±0.9 ＜0.001 Note: * indicates p < 0.01 compared to baseline. Table 2. Comparison of other efficacy indicators index experimental group Control group 1 p-value Borg score decreased 3.8±0.9 1.2±0.6 ＜0.001 Incidence of respiratory muscle fatigue (times / week) 1.3±0.5* 3.9±0.9 ＜0.001 Number of acute exacerbations (4 weeks) 0.4±0.2 1.2±0.4 ＜0.01 Compliance (%) 92.7±5.3 68.4±10.2 ＜0.001 Patient satisfaction (VAS 0-10) 8.7±1.1 5.3±1.8 ＜0.001 Table 3. Verification of Technical Indicators index Experimental verification value (compared to control group 1) p-value Improved sputum clearance efficiency 52.8% ＜0.001 Respiratory muscle fatigue reduction rate 66.7% ＜0.001 Drug deposition rate in the lungs 58.3±5.7% - Training parameter matching accuracy 89.2% - VII. Experimental Conclusions The experimental group had an increase of 18.6 ml (+52.8%) in sputum expectoration over 24 hours, which was significantly higher than that of the control group (p<0.001). CT imaging showed that the sputum clearance rate reached 72.3%, which verified the effectiveness of the "vibration + pulsed airflow" synergistic expectoration mechanism.

[0087] FEV1 increased by 12.5% ​​(p < 0.001), 6MWD increased by 80 meters (+28.3%), SpO2 increased by 4.3%, Borg score decreased by 3.8 points, and the incidence of respiratory muscle fatigue decreased by 66.7%, exceeding the experimental target of 35%.

[0088] The advantages of the intelligent system are evident: the accuracy rate of training parameter matching is 89.2%, the accuracy rate of sputum identification is 92.3%, and the patient compliance rate is 92.7%, which is significantly higher than that of the control group (p<0.001). The number of acute exacerbations is reduced by 67% (0.4: 1.2 times / 4 weeks).

[0089] It exhibits good safety and tolerance, with no serious adverse events occurring and a failure rate of <2%.

[0090] It should be noted that, in this document, relational terms such as "first" and "second" are used only 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 process, method, article, or apparatus.

[0091] The above descriptions are merely embodiments of the present invention. Commonly known structures and characteristics are not described in detail here. Those skilled in the art are aware of all common technical knowledge in the field prior to the application date or priority date, are aware of all existing technologies in that field, and have the ability to apply conventional experimental methods prior to that date. Those skilled in the art can, under the guidance of this application, improve and implement this solution in combination with their own capabilities. Some typical known structures or methods should not be obstacles for those skilled in the art to implement this application. It should be noted that those skilled in the art can make several modifications and improvements without departing from the structure of the present invention. These should also be considered within the scope of protection of the present invention, and will not affect the effectiveness of the implementation of the present invention or the practicality of the patent. The scope of protection claimed in this application should be determined by the content of its claims, and the specific embodiments described in the specification can be used to interpret the content of the claims.

Claims

1. A respiratory medicine clinical pulmonary function rehabilitation device, comprising a shell (1), characterized in that: A strap (7) is fixedly connected to the housing (1). An airway (19) and an nebulizer chamber (8) are opened inside the housing (1). One side of the airway (19) is connected to the nebulizer chamber (8). A breathing resistance component is provided in the airway (19). A drug delivery component is provided in the nebulizer chamber (8). A breathing tube (4) is detachably connected to one end of the airway (19). A mouthpiece (5) is detachably connected to the end of the breathing tube (4). A display controller (3) is fixedly connected to one side of the housing (1). A battery (2) is fixedly connected to the display controller (3). Both the breathing resistance component and the drug delivery component are connected to the display controller (3) via signals. The respiratory resistance component is used to apply resistance to the patient's breathing movements through magnetically controlled damping technology, and promotes the loosening and movement of sputum toward the main bronchus through pulsed airflow generation and chest resonance, in conjunction with the patient's cough reflex to expel it. A drug delivery component for controlling the release rate and particle diameter of the nebulized drug solution based on the patient's inspiratory resistance. The display controller (3) is used to display and select the current respiratory resistance and drug administration parameters, intelligently customize the pulmonary function rehabilitation plan according to the actual respiratory function of the monitored patient, and coordinate the execution of each component.

2. The respiratory medicine clinical pulmonary function rehabilitation device according to claim 1, characterized in that: The display controller (3) includes a monitoring module, a training and matching module, and an output module. The monitoring module is used to monitor the patient's respiratory pressure, flow rate, frequency and blood oxygen data, and to monitor the temperature and humidity data inside the housing (1); The training matching module is used to match appropriate rehabilitation plans and identify sputum viscosity based on the patient data obtained from monitoring using an AI algorithm model; The output module is used to adjust the parameters of each component according to the matched rehabilitation plan, and prompts the patient to correctly execute the rehabilitation plan through the display and voice functions of the display controller (3).

3. The respiratory medicine clinical pulmonary function rehabilitation device according to claim 1, characterized in that: The breathing resistance assembly includes a bellows, with a magnetic sleeve (21) fixedly sleeved on the outside of the bellows. Both ends of the bellows are fixedly connected to both ends of the magnetic sleeve (21). Permanent magnets (32) are symmetrically slidably fitted between the bellows and the magnetic sleeve (21). The corresponding permanent magnets (32) have a repulsive force, so that the bellows is in a semi-expanded state inside the magnetic sleeve. Symmetrical stabilizing holes are opened in the middle of the magnetic sleeve (21). Stabilizing rods are fixedly connected to the middle of the permanent magnets (32). The stabilizing rods pass through the stabilizing holes and slide with the stabilizing holes. The outer wall of the magnetic sleeve (21) is wound with an electromagnetic coil (35). The magnetic sleeve (21) is fixedly connected to the inner wall of the airway (19). The end of the bellows away from the breathing tube (4) is connected to the inhalation check valve (33) and the pulse airflow tube (10). The end of the inhalation check valve (33) away from the breathing tube (4) is connected to the outside. The electromagnetic coil (35) is connected to the display controller (3) signal.

4. The respiratory medicine clinical pulmonary function rehabilitation device according to claim 3, characterized in that: One end of the pulse airflow tube (10) is connected to a conical nozzle (34), and the other end of the pulse airflow tube (10) is connected to an air pump (14). The pulse airflow tube (10) is connected to a bellows. A sampling tube (16) and an exhalation tube are sequentially opened on the inner wall of the airway (19) near the breathing tube (4). An exhalation one-way valve (15) is connected to the end of the exhalation tube. The air pump (14) is connected to the display controller (3) via signal.

5. The respiratory medicine clinical pulmonary function rehabilitation device according to claim 3, characterized in that: The side wall of the housing (1) has several vibration grooves (11), and each vibration groove (11) is equipped with a vibration motor (12). The output shaft of the vibration motor (12) is opposite to that of the display controller (3). An eccentric block (13) is fixedly connected to the output shaft of the vibration motor (12). The vibration motor (12) is connected to the display controller (3) via signal.

6. The respiratory medicine clinical pulmonary function rehabilitation device according to claim 1, characterized in that: The drug delivery assembly includes an atomizing support (22), an atomizing mesh (23) is fixedly connected to the atomizing support (22), the atomizing support (22) is fixedly connected to the side wall of the atomizing chamber (8), a shock-absorbing strip is slidably fitted inside the atomizing support (22), a shock-absorbing rack (30) is fixedly connected to one end of the shock-absorbing strip near the bellows, a stabilizing rack (9) is fixedly connected to the end of the stabilizing rod near the atomizing chamber (8), a reversing gear (29) is provided inside the housing (1), and the shock-absorbing rack (30) and the stabilizing rack (9) are both meshed with the reversing gear (29); A drug chamber (6) is detachably installed inside the atomizing chamber (8). One end of the drug chamber (6) has a drug delivery port, and a silicone valve (27) is installed inside the drug delivery port. A liquid pump (28) is installed on the inner wall of the atomizing chamber (8). The input end of the liquid pump (28) is slidably engaged with the silicone valve (27). The output end of the liquid pump (28) is connected to a nozzle (31), which faces the atomizing mesh (23). The atomizing mesh (23) and the liquid pump (28) are both connected to the display controller (3).

7. The respiratory medicine clinical pulmonary function rehabilitation device according to claim 6, characterized in that: The drug chamber (6) is equipped with a liquid level sensor (26). A conductive diaphragm is slidably fitted between the outer periphery of the liquid pump (28) and the inner wall of the nebulization chamber (8). A conductive switch is embedded in the inner wall of the nebulization chamber (8) on both sides of the conductive diaphragm. A reset spring is fixedly connected to one side of the conductive diaphragm. The reset spring is fixedly connected to the inner wall of the nebulization chamber (8). When the patient inhales and forms a negative pressure in the airway, the conductive diaphragm drives the reset spring to move and connect the power supply of the liquid pump (28) and the nebulization mesh (23) to nebulize the drug liquid. When the patient exhales, the reset spring pulls the conductive diaphragm to reset and cut off the power supply. The liquid level sensor (26) is connected to the display controller (3) for signal connection.

8. The respiratory medicine clinical pulmonary function rehabilitation device according to claim 1, characterized in that: A saliva-proof filter membrane (25) is laid at the connection between the mouthpiece (5) and the breathing tube (4). Both ends of the breathing tube (4) are connected to rotating buckles (20), which are used for the detachable connection between the breathing tube (4) and the airway (19) and the mouthpiece (5).

9. The respiratory medicine clinical pulmonary function rehabilitation device according to claim 2, characterized in that: The monitoring module includes a Hall sensor, a pressure sensor (18), a flow sensor (17), a blood oxygen sensor (24), and a temperature and humidity sensor. The Hall sensor is fixedly connected to the magnetic sleeve (21), the pressure sensor (18) is fixedly connected to the inner wall of the airway (19), the flow sensor (17) is connected to the end of the sampling tube (16), the blood oxygen sensor (24) is fixedly connected to the outer edge of the mouthpiece (5), and the temperature and humidity sensor is fixedly connected to the display controller (3).

10. The respiratory medicine clinical pulmonary function rehabilitation device according to claim 2, characterized in that: The training matching module includes a sputum recognition model and a training decision tree model. A sputum recognition model is used to analyze sputum viscosity based on respiratory pressure waveform images using an LSTM neural network, and to select pulse airflow parameters and vibration motor (12) amplitude. The training decision tree model is used to determine the patient's rehabilitation stage and lung function based on the monitored patient respiratory data, and to match the appropriate training intensity for this stage.

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