Self-adaptive resistance-adjustable intelligent lung rehabilitation training device and control method

Abstract

The invention relates to a self-adaptive resistance-adjustable intelligent lung rehabilitation training device and a control method. The self-adaptive resistance-adjustable intelligent lung rehabilitation training device comprises a tube body, a piston, a magnetic floater, a magnetic resistance mechanism, a motion sensing unit and a controller which are integrated. The piston slides in the pipe in a sealing manner, closes the side wall exhaust hole at the beginning, and opens to exhaust after moving upwards; an air pressure coupling cavity is formed between the magnetic floater and the piston; the magnetic resistance mechanism provides adjustable magnetic force; the motion sensing unit detects piston motion in a non-contact manner. According to the control method, characteristics are extracted by analyzing piston motion signals, the respiratory muscle state of a user is evaluated, the resistance of next expiration is dynamically adjusted, and closed-loop self-adaptive control is formed. The device is simple and reliable in structure, resistance stepless continuous adjustment and personalized safety training are achieved, exhaled airflow does not pass through precise components, and the device is convenient to clean, sanitary and safe.

Description

Technical Field

[0001] This invention relates to the field of medical rehabilitation equipment technology, specifically to an adaptive resistance adjustable intelligent lung rehabilitation trainer and its control method. Background Technology

[0002] Patients with respiratory diseases such as chronic obstructive pulmonary disease and asthma commonly experience respiratory muscle weakness and limited expiratory airflow. One of the core methods of pulmonary rehabilitation training is expiratory muscle training, which involves having patients actively exhale against a certain resistance to enhance the strength and endurance of respiratory muscles (mainly abdominal muscles).

[0003] Currently, expiratory muscle trainers on the market are mainly divided into two categories: Traditional mechanical training devices (such as counterweight-based devices): These devices are typically tubular structures where the user blows air to lift weights (such as steel balls) against gravity. Their technical problems lie in the fact that the resistance is fixed and not continuously adjustable (adjustment is achieved by adding or removing weights), making it impossible to personalize the training to the user's actual ability. First-time users who choose the wrong resistance may find that the training is either too difficult to complete or too difficult to achieve results. More importantly, the resistance remains constant throughout the exhalation process, failing to simulate real physiological load or achieve progressive training. Furthermore, they lack real-time monitoring and protection mechanisms for user fatigue, posing a training risk.

[0004] Emerging electronic intelligent training devices: Some products attempt to achieve adjustable resistance through complex electromechanical structures such as solenoid valves and stepper motors. However, these solutions present new technical challenges: complex system structures, high costs, and reduced reliability. The complex multi-chamber, multi-valve pneumatic path design not only increases manufacturing and maintenance difficulty but also introduces the safety hazard of "pressure buildup" due to valve delays or malfunctions. Furthermore, their control logic largely relies on direct detection of airflow pressure. During training, an exhaust channel must be set up to discharge the gas. This exhaust action causes drastic, instantaneous fluctuations in pressure sensor readings, resulting in low signal-to-noise ratio and poor stability of the acquired pressure signal. This severely interferes with the implementation of precise control algorithms based on pressure feedback, making it difficult to achieve stable and reliable adaptive adjustment.

[0005] In summary, the existing technology faces the following technical challenges: how to achieve personalized lung rehabilitation training with a simple and reliable structure that can automatically and continuously adjust resistance based on the user's real-time status and has fatigue monitoring and protection functions. Summary of the Invention

[0006] In view of this, the purpose of the present invention is to provide an adaptive resistance adjustable intelligent lung rehabilitation trainer and control method that is simple in structure, reliable, and can automatically adjust the resistance of the next exhalation in real time according to the user's exhalation performance, automatically and continuously adjust the resistance according to the user's real-time status, and has fatigue monitoring and protection functions.

[0007] This invention is achieved through the following technical solution: An adaptive resistance-adjustable intelligent lung rehabilitation trainer, comprising: It is an integrated tube with an air inlet at the lower end and at least one exhaust hole on the side wall. A piston, sealed and slidably disposed within the tube near the air inlet, initially closes the exhaust port; A magnetic float is slidably disposed within the tube and located above the piston, forming a pneumatic coupling cavity between the piston and the magnetic float; A magnetic resistance mechanism is provided at the upper end of the tube body and is used to apply an adjustable magnetic force to the magnetic float. A motion sensing unit is used to detect the axial movement state of the piston within the tube in a non-contact manner. The controller is communicatively connected to the motion sensing unit and the magnetic resistance mechanism, and is configured to control the magnetic resistance mechanism to adjust the magnitude of the magnetic force based on the piston motion state information detected by the motion sensing unit.

[0008] Further specifying, the piston is embedded with a first permanent magnet, and the motion sensing unit includes an induction coil wound around the outside of the bottom of the tube, the induction coil being used to detect the induced electromotive force generated when the piston moves.

[0009] Further specifying, the magnetic resistance mechanism includes a drivable slider and a second permanent magnet disposed on the drivable slider. The drivable slider is driven by a motor to change the distance between the second permanent magnet and the magnetic float, thereby adjusting the magnitude of the magnetic force.

[0010] Further specifying, the controller is configured to perform the following steps: Based on the output signal of the motion sensing unit, the motion characteristics of the piston during a single exhalation are determined. The motion characteristics include at least one of the following: the arrival time of the piston when it first arrives at the exhaust port position, the peak velocity of the piston, and the effective holding time of the piston above the exhaust port. At least based on the aforementioned movement characteristics, assess the user's respiratory muscle status; Based on the evaluation results, control commands are generated to adjust the output magnetic force of the magnetic resistance mechanism.

[0011] Further specifying, the controller is specifically configured as follows: When it is determined that the effective holding time exceeds a first threshold, a first control command is generated to increase the magnetic force. When the motion characteristics indicate that the piston oscillates periodically near the exhaust port, a second control command is generated to maintain the magnetic force. When it is determined that the peak velocity of the motion shows a continuous decreasing trend and / or the arrival time shows a continuous increasing trend, a third control command is generated to reduce the magnetic force.

[0012] A control method for the aforementioned adaptive resistance-adjustable intelligent lung rehabilitation trainer includes: S1: The motion sensing unit acquires the real-time motion signal generated by the user driving the piston during a single exhalation; S2: Based on the real-time motion signal, extract the motion features of this exhalation; S3: At least based on the aforementioned motion characteristics, assess the user's respiratory muscle state and determine the target magnetic force value of the magnetic resistance mechanism for the next exhalation; S4: After this exhalation, adjust the magnetic force of the magnetic resistance mechanism to the target magnetic force value.

[0013] Further specifying, in step S2, the motion characteristic includes at least one of the following: the arrival time of the piston when it first arrives at the exhaust port position, the peak velocity of the piston, and the effective holding time of the piston maintaining the position above the exhaust port.

[0014] Further specifying, step S3 includes: If the effective holding time exceeds a preset threshold, the decision is to increase the magnetic force of the next exhalation; If, based on the real-time motion signal, it is determined that the piston oscillates periodically near the exhaust port, then the decision is made to maintain the magnetic force for the next exhalation. If the peak velocity of the movement shows a continuous decreasing trend, and / or the arrival time shows a continuous increasing trend, then the decision is to reduce the magnetic force of the next exhalation.

[0015] Further specifying, in step S1, the real-time motion signal is an induced voltage signal that is proportional to the piston's movement speed; step S2 includes analyzing the induced voltage signal to identify the signal inflection point corresponding to when the piston reaches the exhaust port position.

[0016] Furthermore, in step S3, a comprehensive evaluation and decision are made by combining the historical motion features extracted from the previous N exhalations, where N is an integer greater than or equal to 1.

[0017] The beneficial effects of this invention are as follows: Extremely simplified structure, high reliability, and low cost: Adopting a single-pipe integrated design, the mechanical movement of the piston naturally achieves the switching between "building resistance" and "opening exhaust", eliminating the need for complex multi-chamber, valve and electromagnetic actuator, greatly improving the reliability and durability of the equipment, while significantly reducing manufacturing costs.

[0018] It achieves truly personalized and adaptive training: by analyzing the user's own exhalation movement characteristics, it judges the user's ability boundary and fatigue state in real time, and automatically adjusts the resistance to ensure that each training session is in a safe and efficient load range, solving the problem of fixed resistance in traditional equipment that cannot be adjusted according to the individual and the time.

[0019] It has a built-in fatigue monitoring and safety protection mechanism: by monitoring the decay trend of key motion characteristics such as peak motion speed and effective holding time, the system can identify user fatigue in advance and actively reduce training load, effectively preventing the risks caused by overtraining and improving training safety.

[0020] Stable and reliable control signal: The non-contact piston motion detection based on electromagnetic induction is adopted. The signal is not affected by the violent air pressure fluctuations caused by exhaust action, which provides high-quality and highly stable input data for intelligent decision-making algorithms, ensuring the accuracy and robustness of control logic.

[0021] Other advantages, objectives, and features of the invention will be set forth in part in the description which follows, and in part will be apparent to those skilled in the art from the following examination, or may be learned from practice of the invention. The objectives and other advantages of the invention can be realized and obtained through the following description. Attached Figure Description

[0022] Figure 1 A three-dimensional structural diagram of an adaptive resistance-adjustable intelligent lung rehabilitation trainer; Figure 2 A schematic diagram of the internal structure of an adaptive resistance adjustable intelligent lung rehabilitation trainer; Figure 3 for Figure 2 Enlarged view of A in the middle; Figure 4 A schematic diagram of the second permanent magnet driving structure and its cooperation structure with the magnetic float; Figure 5 This is the control logic diagram for the present invention.

[0023] In the picture: 1. Pipe body; 11. Air inlet; 12. Exhaust port; 2. Piston; 21. Sealing ring; 22. First permanent magnet; 3. Magnetic levitation element; 31. Guide ring; 4. Magnetic resistance mechanism; 41. Motor; 42. Lead screw; 43. Driveable slider; 44. Second permanent magnet; 5. Induction coil; 6. Cover; 61. Guide post. Detailed Implementation

[0024] To make the objectives, technical solutions, and advantages of the embodiments of the present invention clearer, the technical solutions of the embodiments of the present invention will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only some embodiments of the present invention, and not all embodiments. The components of the embodiments of the present invention described and shown in the accompanying drawings can generally be arranged and designed in various different configurations.

[0025] Therefore, the following detailed description of the embodiments of the invention provided in the accompanying drawings is not intended to limit the scope of the claimed invention, but merely to illustrate selected embodiments of the invention. All other embodiments obtained by those skilled in the art based on the embodiments of the invention without inventive effort are within the scope of protection of the invention.

[0026] It should be noted that similar labels and letters in the following figures indicate similar items. Therefore, once an item is defined in one figure, it does not need to be further defined and explained in subsequent figures.

[0027] In the above description of the present invention, it should be noted that the terms "one side," "the other side," etc., indicate the orientation or positional relationship based on the orientation or positional relationship shown in the accompanying drawings, or the orientation or positional relationship in which the product of the invention is conventionally placed during use. These terms are used only for the convenience of describing the present invention and for simplifying the description, and do not indicate or imply that the device or element referred to must have a specific orientation, or be constructed and operated in a specific orientation. Therefore, they should not be construed as limitations on the present invention. Furthermore, the terms "first," "second," etc., are used only to distinguish descriptions and should not be construed as indicating or implying relative importance.

[0028] Furthermore, terms such as "identical" do not imply that components must be absolutely identical; minor differences are permissible. The term "perpendicular" simply means that the positional relationship between components is more perpendicular than "parallel," not that the structure must be perfectly perpendicular; a slight tilt is acceptable.

[0029] Please see Figure 1-2 This invention provides a technical solution: an adaptive resistance adjustable intelligent lung rehabilitation trainer, comprising: The tube body 1 is an integral unit, with an air inlet 11 at its lower end and at least one exhaust hole 12 on its side wall. Piston 2 is sealed and slidably disposed inside the tube 1 near the air inlet 11, initially sealing the exhaust port 12; The magnetic float 3 is slidably disposed inside the tube 1 and located above the piston 2, and a pneumatic coupling cavity is formed between the piston 2 and the magnetic float 3; A magnetic resistance mechanism 4 is disposed at the upper end of the tube body 1 and is used to apply an adjustable magnetic force to the magnetic float 3. A motion sensing unit is used to detect the axial movement state of the piston 2 within the tube 1 in a non-contact manner; The controller 6 is communicatively connected to the motion sensing unit and the magnetic resistance mechanism 4, and is configured to control the magnetic resistance mechanism 4 to adjust the magnitude of the magnetic force based on the piston motion state information detected by the motion sensing unit.

[0030] in: The tube body 1 is made of transparent medical-grade polycarbonate with a smooth inner wall. Its lower end is equipped with a standard mouthpiece interface 11 for connecting a hose or other device for the user to blow air, and a ring of evenly distributed exhaust holes 12 is machined in the middle of the side wall.

[0031] Piston 2 is made of lightweight engineering plastic and has a silicone sealing ring 21 embedded on its outer periphery to ensure a seal with the inner wall of tube 1. A cylindrical neodymium iron boron first permanent magnet 22 (magnetized in the axial direction) is embedded in the center of piston 2.

[0032] The magnetic float 3 is a neodymium iron boron magnet assembly with an outer guide ring 31. It is sealed to the inner wall of the tube body 1 and can slide freely.

[0033] The top magnetic mechanism 4 is fixed to the cover 6 at the upper end of the tube body 1.

[0034] It includes a miniature stepper motor 41, with a lead screw 42 coaxially connected to its output shaft and extending downward into the tube body. A driveable slider 43 is threadedly connected to the lead screw 42, and a second permanent magnet 44 is fixed on the driveable slider 43. The cover 6 is also provided with at least one guide post 61 extending parallel to the lead screw 42. By controlling the rotation of the stepper motor through a controller, the distance between the second permanent magnet 44 and the top surface of the magnetic float 3 inside the tube can be precisely adjusted, thereby achieving stepless and linear adjustment of the magnitude of the magnetic repulsion force.

[0035] The controller integrates a microprocessor (such as the STM32G4 series), motor drive circuit, signal acquisition circuit and communication module, and is fixed inside the device housing. It has information storage, signal reception and transmission functions.

[0036] An induction coil 5 is tightly wound at the bottom of the tube 1, corresponding to the initial position of the piston 2, and together with the first permanent magnet 22 embedded on the piston 2, it forms a motion sensing unit. The two ends of the induction coil 5 are connected to the signal acquisition circuit on the controller 6.

[0037] The movement trajectory of piston 2 is as follows: at the instant when the exhaled gas pushes piston 2 upward to expose exhaust port 12, the exhalation pressure will be released instantaneously, and piston 2 will seal exhaust port 12 again. During continuous exhalation, the above state will be continuously cycled, and the induced voltage generated by induction coil 5 will also be in a continuous periodic change, that is, the movement state of piston 2 will be converted into the voltage change of induced current. In use, the user blows air through the air inlet 11 at the bottom, pushing the internally sealed piston 2 upwards. Initially, piston 2 seals the exhaust port 12 on the side wall. When piston 2 is pushed beyond the exhaust port 12, the port opens, allowing exhaled air to be continuously discharged, forming a closed "pneumatic coupling chamber" between the magnetic float 3 above piston 2 and piston 2. The upward movement of piston 2 compresses this chamber, using air pressure to drive the magnetic float 3 upwards synchronously. As the magnetic float 3 moves upwards, it needs to overcome the adjustable magnetic force applied by the magnetic resistance mechanism 4 at the upper end of the tube 1. Therefore, the total resistance that the user needs to overcome during exhalation is essentially the effort required to drive piston 2 to compress the gas and thus push the magnetic float against the magnetic force. A motion sensing unit non-contactly monitors the motion state (such as displacement or velocity) of piston 2 and transmits the signal to the controller. The controller analyzes the user's exhalation performance based on this signal and dynamically adjusts the output of the magnetic resistance mechanism 4, thereby changing the resistance of the next exhalation.

[0038] This technical solution simultaneously achieves the two core functions of "resistance generation" and "gas discharge" in an extremely simple mechanical manner, completely eliminating the need for the multi-cavity, solenoid valve, and other fault-prone components required by the complex electronic trainers in the background technology, and solving their technical problems of "complex structure, high cost, and low reliability". At the same time, it provides a physical basis for resistance adjustment based on real-time user performance.

[0039] Furthermore, the user's exhaled airflow path is clear and concise: it enters through the air inlet 11, pushes the piston 2, and exits through the exhaust port on the side wall, without flowing through the dry area where core precision components such as the magnetic resistance mechanism 4 and the motion sensing unit 5 are located. This "dry and wet separation" flow channel design, along with the detachable and washable mouthpiece interface, greatly reduces the risk of contamination and corrosion of internal components by saliva and moisture, making the device easy to clean and disinfect, effectively ensuring hygiene and safety during use, and solving the pain point of traditional complex air circuit devices being difficult to clean thoroughly.

[0040] In this embodiment, the piston 2 is embedded with a first permanent magnet 22, and the motion sensing unit 5 includes an induction coil wound around the outside of the bottom of the tube 1. The induction coil is used to detect the induced electromotive force generated when the piston 2 moves.

[0041] A first permanent magnet 22 is embedded inside the piston 2, and an induction coil 5 is fixedly wound around the bottom outer side of the tube 1. According to Faraday's law of electromagnetic induction, when the piston 2 with the embedded magnet moves inside the tube, it cuts the magnetic field lines of the induction coil 5, generating an induced electromotive force at both ends of the coil. The magnitude of this electromotive force is proportional to the instantaneous velocity of the piston 2, and its polarity reflects the direction of motion. The aforementioned sensing method is completely non-contact and wear-free, and the induction coil 5 is located outside the tube body 1, physically isolated from the internal airflow and the exhaust port 12 area, and is not affected by any severe pressure fluctuations during exhaust. This solves the core problem in the background technology that "the pressure signal fluctuates violently due to the exhaust action, resulting in a low signal-to-noise ratio and seriously interfering with precise control," providing the controller with a stable, reliable, and high-quality feedback signal.

[0042] In this embodiment, the magnetic resistance mechanism 4 includes a drivable slider 43 and a second permanent magnet 44 disposed on the drivable slider 43. The drivable slider 43 is driven by a motor 41 to change the distance between the second permanent magnet 44 and the magnetic float 3, thereby adjusting the magnitude of the magnetic force.

[0043] One specific implementation of the magnetic resistance mechanism 4 is as follows: the motor 41 can be a miniature stepper motor, which drives a drivable slider 43, on which a second permanent magnet 44 is fixed. The controller, by controlling the rotation angle and direction of the motor 41, can drive the drivable slider 43 to move linearly, thereby precisely adjusting the distance between the second permanent magnet 44 and the top surface of the magnetic float 3 inside the tube 1. Based on the physical principle that the magnitude of magnetic force is inversely proportional to the distance, even a small change in distance can cause a significant and continuous change in the magnetic force acting on the magnetic float 3, achieving a leap from "stepped adjustment" to "stepless, linear, and continuously adjustable" resistance. This directly contrasts with the problem in the background technology that "traditional mechanical trainers have fixed resistance or only a few levels, unable to precisely adapt to the user's ability." The motor-driven adjustment method lays the hardware foundation for achieving fully automatic and programmed resistance control.

[0044] In this embodiment, the controller is configured to perform the following steps: Based on the output signal of the motion sensing unit 5, the motion characteristics of the piston 2 during a single exhalation are determined. The motion characteristics include at least one of the following: the arrival time of the piston 2 when it first arrives at the position of the exhaust port 12, the peak velocity of the piston 2, and the effective holding time of the piston 2 above the exhaust port 12. At least based on the aforementioned movement characteristics, assess the user's respiratory muscle status; Based on the evaluation results, control commands are generated to adjust the output magnetic force of the magnetic resistance mechanism 4.

[0045] The core algorithm of the controller is as follows: First, it processes the raw signal from the motion sensing unit, i.e., the induced voltage of the induction coil, and converts it into interpretable motion features through calculation (e.g., integration, differentiation). These features directly reflect the user's physiological performance: arrival time reflects initial explosive force; peak velocity reflects maximum muscle strength output; and effective hold time reflects muscle endurance. Based on these objective features, it assesses whether the user is currently "capable," "under appropriate load," or "fatigued," and accordingly makes decisions to "increase resistance," "maintain resistance," or "decrease resistance," generating corresponding control commands and sending them to the magnetic resistance mechanism 4, shifting from "device-driven" to "user-state-driven." This solves the fundamental problem in the background technology that "devices cannot be personalized according to the user's actual ability," ensuring that each training load can dynamically match the user's real-time physiological state, thereby improving the safety and effectiveness of training.

[0046] In this embodiment, the controller is specifically configured as follows: When it is determined that the effective holding time exceeds a first threshold, a first control command is generated to increase the magnetic force. When the motion characteristics indicate that the piston 2 oscillates periodically near the exhaust port 12, a second control command is generated to maintain the magnetic force. When it is determined that the peak velocity of the motion shows a continuous decreasing trend and / or the arrival time shows a continuous increasing trend, a third control command is generated to reduce the magnetic force.

[0047] When piston 2 remains stable above exhaust port 12 for an extended period (effective holding time is long), it indicates that the current resistance is too low and the training intensity is insufficient. Therefore, the first control command is triggered to increase the resistance to maintain the training effect. When piston 2 oscillates periodically near exhaust port 12, it indicates that the user's strength and the current resistance are at a precise balance point, representing an ideal training load state. Therefore, the second control command is triggered to maintain the resistance. When a continuous decrease in peak speed or a continuous increase in arrival time is detected, which are typical electromechanical manifestations of muscle fatigue, the system provides an early warning and actively triggers the third control command to reduce the resistance to prevent overtraining, achieving the dual goals of adaptive training and active safety protection. It not only dynamically optimizes training intensity but also proactively addresses the safety hazard of the trainer in the background technology that "lacks a real-time monitoring and protection mechanism for the user's fatigue state," giving the device "overload protection" intelligence.

[0048] Please see Figure 3A control method for the aforementioned adaptive resistance-adjustable intelligent lung rehabilitation trainer includes: S1: The motion sensing unit acquires the real-time motion signal generated by the user driving the piston 2 during a single exhalation; S2: Based on the real-time motion signal, extract the motion features of this exhalation; S3: At least based on the aforementioned motion characteristics, assess the user's respiratory muscle state and determine the target magnetic force value of the magnetic resistance mechanism 4 for the next exhalation; S4: After this exhalation, adjust the magnetic force of the magnetic resistance mechanism 4 to the target magnetic force value.

[0049] In this embodiment, in step S2, the motion characteristics include at least one of the following: the arrival time of the piston 2 when it first arrives at the position of the exhaust port 12, the peak velocity of the piston 2, and the effective holding time of the piston 2 above the exhaust port 12.

[0050] Specifically, step S3 includes: If the effective holding time exceeds a preset threshold, the decision is to increase the magnetic force of the next exhalation; If, based on the real-time motion signal, it is determined that the piston 2 oscillates periodically near the exhaust port 12, then the decision is made to maintain the magnetic force for the next exhalation. If the peak velocity of the movement shows a continuous decreasing trend, and / or the arrival time shows a continuous increasing trend, then the decision is to reduce the magnetic force of the next exhalation.

[0051] During a single exhalation (S1, S2), the system does not act but only records, fully acquiring the piston movement signal and extracting its features. During the interval after exhalation (S3), the system analyzes and plans, making evaluations and decisions based on the newly acquired data. Before the next exhalation begins (S4), the system executes, pre-setting the resistance to a new target value. The entire cycle is seamlessly connected, following the user's breathing rhythm, defining a closed loop for human-machine interaction.

[0052] This method breaks down complex adaptive control into clear steps that are fully synchronized with the user's respiratory physiological rhythm, achieving an intelligent closed loop of "assessment-adjustment-reassessment." This systematically solves the problems of rigidity and lack of feedback in traditional equipment training processes, turning each exhalation into a personalized ability assessment and prescription adjustment.

[0053] In this embodiment, in step S1, the real-time motion signal is an induced voltage signal that is proportional to the movement speed of the piston 2; step S2 includes analyzing the induced voltage signal to identify the signal inflection point corresponding to when the piston 2 reaches the position of the exhaust port 12.

[0054] The induced voltage is a direct measurement. By identifying specific "inflection points" (such as a turning point from rising to rapidly falling) on ​​the induced voltage signal waveform, the controller can accurately determine the exact moment when piston 2 reaches exhaust port 12. This is because when the piston opens the exhaust port, the high-pressure gas inside the chamber is suddenly released, causing a sudden change in the piston's acceleration, and this physical event leaves a clear imprint on the velocity signal.

[0055] Using the characteristic manifestations of physical events on sensor signals to determine key points is more robust and accurate than relying on absolute displacement calibration. This further enhances the advantage of this scheme in using stable, feature-rich motion signals to replace unstable pressure signals, ensuring the accuracy of control timing.

[0056] In this embodiment, in step S3, a comprehensive evaluation and decision are made by combining the historical motion features extracted from the previous N exhalations, where N is an integer greater than or equal to 1.

[0057] When making decisions, the controller does not view single exhalation data in isolation, but maintains a historical data window containing the characteristics of the most recent N (e.g., 3) exhalations. By analyzing the trends of these characteristics within the window (such as whether peak velocity decreases for three consecutive beats), it distinguishes between normal fluctuations in ability and true fatigue trends. By introducing historical trend analysis, the system acquires "short-term memory" and "trend prediction" capabilities. Effectively filtering out interference data from single exhalations that may be caused by user distraction, coughing, or other accidental factors significantly improves the accuracy and fault tolerance of fatigue state assessment, making adaptive adjustment smoother and more reasonable, resulting in a better user experience. This solves the problem of erroneous adjustment caused by data noise in simple threshold control.

[0058] Specifically, it comprehensively assesses the user's real-time capabilities and fatigue level, and determines the target resistance value for the next exhalation accordingly.

[0059] The decision-making logic is as follows: Set the initial resistance value for the magnetic resistance mechanism. The user is ready to begin their first exhalation training.

[0060] Real-time data acquisition and feature extraction: During a user's single exhalation, a motion sensing unit continuously acquires real-time signals (induced voltage) reflecting the piston's motion state. Based on these signals, key motion features of this exhalation are calculated or extracted, including but not limited to: Arrival time: The time elapsed from the start of exhalation until piston 2 first reaches the position of exhaust port 12. This event can be identified by the first characteristic inflection point of the piston 2 speed signal.

[0061] Peak velocity: The maximum instantaneous velocity reached by piston 2 during this exhalation.

[0062] Effective holding time: The cumulative time that piston 2 remains above exhaust port 12 and keeps exhaust port 12 unobstructed can be evaluated by the duration of the stable segment of the speed signal near zero.

[0063] Fluctuation characteristics: When piston 2 oscillates near exhaust port 12, the oscillation frequency and amplitude of the speed signal.

[0064] If the effective holding time consistently exceeds the preset threshold, and the peak motion speed remains stable or increases, then the user is deemed to have sufficient ability, and the decision is to "increase resistance". Target resistance value = current damping value × (1 + α), where α is a small increment coefficient (e.g., 5%).

[0065] If the speed signal shows that piston 1 exhibits stable and regular oscillations near exhaust port 12, it is determined that the user is in an ideal training load state, and the decision is "maintain resistance": target resistance value = current damping value.

[0066] If the peak velocity decreases continuously, and / or the arrival time increases continuously, and / or the effective holding time decreases significantly, the user is considered fatigued, and the decision is to "reduce resistance": target resistance value = current damping value * β, where β is a resistance reduction coefficient less than 1 (e.g., 0.8).

[0067] Resistance preset: During the interval between the end of exhalation and the user's inhalation, the controller sends a command to the magnetic resistance mechanism to adjust its resistance output to the target resistance value obtained in step S3.

[0068] Loop execution: Return to step S2, and perform a new round of data collection, evaluation and adjustment for the user's next exhalation, forming a closed-loop adaptive control loop of "evaluation-adjustment-re-evaluation".

[0069] That is, by analyzing the motion signal of piston 2 to extract features, the user's respiratory muscle state is assessed, and the resistance of the next exhalation is dynamically adjusted to form a closed-loop adaptive control. The structure is simple and reliable, realizing stepless continuous adjustment of resistance and personalized safe training. Moreover, the exhaled airflow does not pass through precision components, making it easy to clean and hygienic.

[0070] Finally, it should be noted that the above embodiments are only used to illustrate the technical solutions of the present invention and are not intended to limit it. Although the present invention has been described in detail with reference to preferred embodiments, those skilled in the art should understand that modifications or equivalent substitutions can be made to the technical solutions of the present invention without departing from the spirit and scope of the technical solutions of the present invention, and all such modifications or substitutions should be covered within the scope of the claims of the present invention.

Claims

1. An intelligent lung rehabilitation trainer with adaptive resistance adjustment, characterized in that, include: It is an integrated tube with an air inlet at the lower end and at least one exhaust hole on the side wall. A piston, sealed and slidably disposed within the tube near the air inlet, initially closes the exhaust port; A magnetic float is slidably disposed within the tube and located above the piston, forming a pneumatic coupling cavity between the piston and the magnetic float; A magnetic resistance mechanism is provided at the upper end of the tube body and is used to apply an adjustable magnetic force to the magnetic float. A motion sensing unit is used to detect the axial movement state of the piston within the tube in a non-contact manner. The controller is communicatively connected to the motion sensing unit and the magnetic resistance mechanism, and is configured to control the magnetic resistance mechanism to adjust the magnitude of the magnetic force based on the piston motion state information detected by the motion sensing unit.

2. The adaptive resistance adjustable intelligent lung rehabilitation trainer according to claim 1, characterized in that, The piston has a first permanent magnet embedded in it, and the motion sensing unit includes an induction coil wound around the outside of the bottom of the tube. The induction coil is used to detect the induced electromotive force generated when the piston moves.

3. The adaptive resistance adjustable intelligent lung rehabilitation trainer according to claim 1 or 2, characterized in that, The magnetic resistance mechanism includes a driveable slider and a second permanent magnet disposed on the driveable slider. The driveable slider is driven by a motor to change the distance between the second permanent magnet and the magnetic float, thereby adjusting the magnitude of the magnetic force.

4. The adaptive resistance adjustable intelligent lung rehabilitation trainer according to claim 1, characterized in that, The controller (6) is configured to perform the following steps: Based on the output signal of the motion sensing unit, the motion characteristics of the piston during a single exhalation are determined. The motion characteristics include at least one of the following: the arrival time of the piston when it first arrives at the exhaust port position, the peak velocity of the piston, and the effective holding time of the piston above the exhaust port. At least based on the aforementioned movement characteristics, assess the user's respiratory muscle status; Based on the evaluation results, control commands are generated to adjust the output magnetic force of the magnetic resistance mechanism.

5. The adaptive resistance adjustable intelligent lung rehabilitation trainer according to claim 4, characterized in that, The controller is specifically configured as follows: When it is determined that the effective holding time exceeds a first threshold, a first control command is generated to increase the magnetic force. When the motion characteristics indicate that the piston oscillates periodically near the exhaust port, a second control command is generated to maintain the magnetic force. When it is determined that the peak velocity of the motion shows a continuous decreasing trend and / or the arrival time shows a continuous increasing trend, a third control command is generated to reduce the magnetic force.

6. A control method for an adaptive resistance-adjustable intelligent lung rehabilitation trainer according to any one of claims 1 to 3, characterized in that, include: S1: The motion sensing unit acquires the real-time motion signal generated by the user driving the piston during a single exhalation; S2: Based on the real-time motion signal, extract the motion features of this exhalation; S3: At least based on the aforementioned motion characteristics, assess the user's respiratory muscle state and determine the target magnetic force value of the magnetic resistance mechanism for the next exhalation; S4: After this exhalation, adjust the magnetic force of the magnetic resistance mechanism to the target magnetic force value.

7. The control method according to claim 6, characterized in that, In step S2, the motion characteristics include at least one of the following: the arrival time of the piston when it first arrives at the exhaust port position, the peak velocity of the piston, and the effective holding time of the piston above the exhaust port.

8. The control method according to claim 7, characterized in that, Step S3 includes: If the effective holding time exceeds a preset threshold, the decision is to increase the magnetic force of the next exhalation; If, based on the real-time motion signal, it is determined that the piston oscillates periodically near the exhaust port, then the decision is made to maintain the magnetic force for the next exhalation. If the peak velocity of the movement shows a continuous decreasing trend, and / or the arrival time shows a continuous increasing trend, then the decision is to reduce the magnetic force of the next exhalation.

9. The control method according to claim 6, characterized in that, In step S1, the real-time motion signal is an induced voltage signal that is proportional to the piston's movement speed; step S2 includes analyzing the induced voltage signal to identify the signal inflection point corresponding to when the piston reaches the exhaust port position.

10. The control method according to any one of claims 6 to 9, characterized in that, In step S3, a comprehensive evaluation and decision are made by combining the historical motion features extracted from the previous N exhalations, where N is an integer greater than or equal to 1.

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