Active detection device for respiratory trainer, multifunctional inhalation trainer and method

Abstract

The present application relates to the technical field of medical equipment, and discloses an active detection device of a breathing training device, a multifunctional inhalation training device and a method, wherein the multifunctional inhalation training device acquires parameters such as breathing frequency and / or single continuous operation duration and / or cumulative use frequency of a breathing valve through a first detector, since the operation parameters of the breathing valve correspond to the training parameters of a patient, thereby realizing real-time collection of multiple key physiological parameters such as breathing frequency, single training duration and cumulative use frequency of the user; the user can check the use data at any time, so that when people use the multifunctional inhalation training device, they can understand their own use condition through intuitive data, and thus know whether the use data meets the standard.

Description

Technical Field

[0001] This invention relates to the field of medical device technology, specifically to an active detection device for a breathing trainer, a multifunctional inspiratory trainer, and a method thereof. Background Technology

[0002] Patent application publication number CN120571212A discloses a multifunctional breathing training device that implements a nasal inhalation and mouth exhalation breathing training mode. It also discloses a technical means to adjust resistance by combining a breathing valve with a resistance unit. The resistance unit uses a first magnet and a static magnet in combination. The magnetic attraction between the two causes the breathing valve to return to the through hole and close the passage. At the same time, it can also provide a certain training resistance. That is, the user needs to provide a larger inhalation training airflow to open the breathing valve, thereby achieving a better effect of training the inspiratory muscles. During use, the airflow pushes the first magnet to generate high-frequency micro-amplitude vibration. The high-frequency vibration can make the first magnet move up and down.

[0003] Since the solution cannot view or obtain usage data and status in real time, a detection device was designed to collect relevant physiological parameters and usage data of users during breathing training. Summary of the Invention

[0004] The purpose of this invention is to provide an active detection device for a breathing trainer, which acquires the breathing parameters of the breathing valve, thereby enabling real-time collection of multiple key physiological parameters such as the user's breathing rate, single training duration, and cumulative number of uses, allowing the user to conveniently view the usage data at any time.

[0005] To achieve the above objectives, the present invention adopts the following technical solution: An active detection device for a breathing trainer includes: at least one first detector and a controller.

[0006] The at least one first detector is used to acquire information on magnetic field changes and / or vibration information of the breathing trainer.

[0007] The controller is configured to be electrically connected to the at least one first detector.

[0008] The controller calculates the breathing frequency and / or single continuous operation duration and / or cumulative number of uses of the breathing valve based on the information obtained by the at least one first detector.

[0009] The active detection device of the breathing trainer provided in at least one embodiment of this disclosure further includes a storage battery.

[0010] The battery is used to power the controller and the first detector.

[0011] In the active detection device of the breathing trainer provided in at least one embodiment of this disclosure, the controller includes: a flexible circuit board and a microcontroller unit.

[0012] The microcontroller unit is configured to be electrically connected to the flexible circuit board.

[0013] Both the first detector and the battery are configured to be electrically connected to the flexible circuit board.

[0014] The active detection device of the breathing trainer provided in at least one embodiment of this disclosure further includes: a wireless communication module.

[0015] The wireless communication module is used to communicate with at least one terminal.

[0016] The controller transmits the calculated information to at least one terminal via the wireless communication module.

[0017] The active detection device for a breathing trainer provided in at least one embodiment of this disclosure further includes an input module and an output module.

[0018] The input module is used to generate and send control commands to the controller.

[0019] The output module is used at least to display the calculation results of the controller.

[0020] The controller, according to the control command, at least controls itself to shut down or turn on.

[0021] In the active detection device of the breathing trainer provided in at least one embodiment of this disclosure, the first detector includes a Hall linear sensor and / or a triaxial accelerometer.

[0022] The active detection device of the breathing trainer provided in at least one embodiment of this disclosure further includes at least one second detector.

[0023] The at least one second detector is used to acquire information on airflow changes within the breathing trainer.

[0024] The at least one second detector is configured to be electrically connected to the controller, and the controller determines the working status of the breathing valve based on the information obtained by the at least one second detector.

[0025] Secondly, the present invention also provides a multifunctional breathing trainer, including a breathing valve and an active detection device for the aforementioned breathing trainer. The breathing valve has a valve seat and a valve plate, which are movably connected, and a first magnet is disposed on the valve plate.

[0026] The multifunctional inhalation trainer provided in at least one embodiment of this disclosure further includes a support body.

[0027] The support structure is used to provide support for the first detector and controller.

[0028] The support body is provided with a magnetic attraction component, and a second magnet is fixedly provided inside the valve seat.

[0029] The second magnet has the opposite polarity to the magnetic attraction component, and the support is magnetically connected to the outside of the valve seat through the magnetic attraction component and the second magnet.

[0030] The first magnet has opposite polarities to the second magnet.

[0031] In at least one embodiment of the multifunctional breathing trainer provided in this disclosure, the magnetic component is a magnetic charging base, which is used to connect a charging current to charge the battery.

[0032] In at least one embodiment of the multifunctional breathing trainer provided in this disclosure, a breathing mask is provided at the air inlet end of the breathing valve.

[0033] The support is arranged in a ring shape and is sleeved on the outer periphery of the breathing valve.

[0034] The exhaust end of the breathing valve is provided with a funnel-shaped limiting part, which cooperates with the breathing mask to prevent the support from falling off the breathing valve.

[0035] The identification method for a multifunctional inhalation trainer provided in at least one embodiment of this disclosure includes the following steps: 1) Take a lower value and a higher value from the analog signal of the first detector. The lower value is... The higher value ; Under static conditions, the first detector will identify the value of an analog signal. ; When the multi-functional breathing trainer is lightly touched, the first detector will recognize a value of an analog signal. ; Under conditions of subtle use, the first detector will identify a value of an analog signal. ; When the multi-functional breathing trainer is used normally, the first detector will identify a value of an analog signal. ; Under conditions where the multi-functional breathing trainer is used extensively, the first detector will identify a value of an analog signal. ; Among them, it is set as ; 2) The value of the analog signal detected by the first detector is reduced from below a certain value within one usage cycle. to higher This process is unique within a single usage cycle. The controller detects that the multi-functional breathing trainer is being used. When the value of the analog signal detected by the first detector increases from higher than [value] within a usage cycle to below This process is unique within a single usage cycle, and the controller determines that the multi-functional inhalation trainer has reached the end of its use. Since the entire breathing process is divided into exhalation and inhalation, the multi-functional breathing trainer generates air pressure during exhalation, which can be detected by the first detector. However, no signal is generated during inhalation. The controller uses a periodic detection method to check whether the multi-functional breathing trainer is being used. If it is detected within a set period, the controller adds another period to the time. If it is detected at any second within the period, the controller adds another period to the total time. The relationship is as follows: , For natural numbers, One respiratory cycle is measured in seconds, t = 5 ± 2 s.

[0036] The beneficial effects of this invention are as follows: Since the operating parameters of the breathing valve correspond to the patient's training parameters, by setting a first detector to obtain the operating parameters of the breathing valve, it is possible to collect multiple key physiological parameters such as the user's respiratory rate, single training duration, and cumulative number of uses in real time, thereby realizing dynamic monitoring and data visualization of the breathing training process, helping users to scientifically adjust the training rhythm, and improving the user experience and training effect. Attached Figure Description

[0037] To more clearly illustrate the technical solutions in the embodiments of the present invention, the accompanying drawings used in the description of the embodiments will be briefly introduced below. Obviously, the accompanying drawings described below are only some embodiments of the present invention. For those skilled in the art, other drawings can be obtained based on these drawings without creative effort.

[0038] Figure 1 This is a cross-sectional view of the active detection device of the breathing trainer in Example 1.

[0039] Figure 2 This is an exploded perspective view of some components in Example 1.

[0040] Figure 3 This is a schematic diagram of the structure after some components in Example 1 are assembled into the outer frame.

[0041] Figure 4 This is a cross-sectional view of the active detection device of the breathing trainer in Examples 2 and 5.

[0042] Figure 5 This is a perspective view of the multifunctional inhalation trainer in Example 3.

[0043] Figure 6 The graph shows the change in magnetic flux density generated by the first magnet itself as a function of distance.

[0044] Figure 7 This is a schematic diagram of Hall sensing in a Hall linear sensor.

[0045] Figure 8 This is a block diagram showing the connection of some electronic components of the active detection device in a breathing trainer.

[0046] Figure 9 This is a cross-sectional view of the active detection device of the breathing trainer in Example 6.

[0047] Figure 10 This is a schematic diagram of the structure of the multifunctional inhalation trainer in Example 7.

[0048] In the picture: 10. Breathing valve; 101. Valve seat; 102. Valve plate; 103. First magnet; 111. Second magnet; 12. First detector; 13. Controller; 131. Flexible circuit board; 132. Microcontroller unit; 14. Support body; 141. Magnetic suction component; 142. Outer frame; 143. Epoxy resin adhesive layer; 15. Battery; 16. Output module; 17. Second detector; 20. Breathing mask; 21. Limiting part; 30. Active detection device. Detailed Implementation

[0049] The technical solutions in the embodiments will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only some embodiments, not all embodiments.

[0050] Currently, there is no corresponding detection scheme for the breathing valve used in inhalation trainers, which makes it impossible to view or obtain usage data and status in real time during use. Therefore, this embodiment proposes an active detection device for inhalation trainers. When people use inhalation trainers, they can understand their own usage through intuitive data, thereby knowing whether the usage data meets the standards.

[0051] Example 1 like Figure 1 and 2As shown, this embodiment provides an active detection device for a breathing trainer, including: a breathing valve 10, a first detector 12, a controller 13, a support 14, a battery 15, a wireless communication module (not shown), an input module (not shown), and an output module 16.

[0052] The breathing valve 10 has a valve seat 101 and a valve plate 102, which are movably connected. A first magnet 103 is provided on the valve plate 102.

[0053] The first detector 12 is used to acquire motion information of the first magnet 103. The controller 13 calculates the respiratory rate, single continuous operation duration, and cumulative number of uses of the breathing valve 10 based on the information acquired by the first detector 12. Since the operating parameters of the breathing valve correspond to the patient's training parameters, this enables real-time acquisition of several key physiological parameters, such as the user's respiratory rate, single training duration, and cumulative number of uses.

[0054] In this embodiment, a magnetic attraction component 141 is provided on the support body 14, and a second magnet 111 is fixedly provided inside the valve seat 101. The second magnet 111 has the opposite polarity to the magnetic attraction component 141, and the support body 14 is magnetically connected to the outside of the valve seat 101 through the magnetic attraction component 141 and the second magnet 111. The first magnet 103 has the opposite polarity to the second magnet 111.

[0055] In this embodiment, the battery 15 is used to power the controller 13 and the first detector 12.

[0056] In this embodiment, the controller 13 includes a flexible circuit board 131 and a microcontroller unit 132.

[0057] Specifically, the first detector 12, the battery 15, the wireless communication module, the input module, the output module 16, and the microcontroller unit 132 are all electrically connected to the flexible circuit board 131.

[0058] Specifically, the wireless communication module is used to communicate with the terminal, and the controller 13 can transmit the calculated information to the terminal through the wireless communication module.

[0059] Specifically, the input module is used to generate and send control commands to the controller 13. The output module 16 displays the calculation results of the controller 13.

[0060] Specifically, the controller 13 controls itself to shut down or turn on according to the control command.

[0061] Specifically, the magnetic component 141 is a magnetic charging base, which is used to receive charging current to charge the battery 15. The magnetic charging base is electrically connected to the flexible circuit board 131.

[0062] The following section will disclose the specific structure of the support component and its connection structure with other components, in conjunction with the accompanying drawings.

[0063] like Figure 2 and 3 As shown, the support body 14 includes an outer frame 142, which is arranged in a ring shape. The outer frame 142 is preferably made of materials with excellent mechanical strength, corrosion resistance and thermal stability, such as plastic, stainless steel, ceramic, and titanium steel, to adapt to complex and changing usage environments. The outer frame 142 not only protects the internal components, but also undertakes multiple functions such as heat dissipation, electromagnetic shielding and structural support.

[0064] The battery 15, output module 16 and flexible circuit board 131 are all arc-shaped; the flexible circuit board 131 and the battery 15 are both fixed on the inner ring surface of the outer frame 142.

[0065] The output module 16 uses a touch screen, which is embedded in the assembly port, while the input module extends to the outside through the assembly port.

[0066] The wireless communication module, the magnetic charging base, and the first detector 12 are integrated on the flexible circuit board 131, and the magnetic charging base and the first detector 12 are arranged horizontally opposite each other.

[0067] To further enhance overall stability, after the components are assembled into the outer frame 142 and pass inspection, they enter the sealing and encapsulation process. Epoxy resin is injected through a curing mold and cured under specific temperature and time conditions to form an epoxy resin layer 143. This achieves complete filling and airtight sealing of the outer frame 142, effectively eliminating residual air and creating a tightly sealed enclosure with no internal air or gaps. This greatly improves the module's reliability, vibration resistance, and long-term service life.

[0068] To ensure magnetic stability and electrical connection, the magnetic charging base adopts a male type, with the pin ends located outside the epoxy resin adhesive layer 143. The epoxy resin adhesive layer 143 also has a ring-shaped structure.

[0069] The electronic components inside the epoxy resin adhesive layer 143 are arranged in a regular circumferential distribution, starting from the magnetic charging base and proceeding clockwise. The first part is the magnetic charging base, which serves as the module's energy input interface, responsible for magnetic alignment with external charging devices and conducting electrical energy. The second part, following closely behind, is the battery 15, which serves as the core of the module's energy storage, providing continuous and stable operating power. The third part is the first detector 12, used to detect changes in the breathing valve parameters to achieve position sensing or status recognition functions. The fourth part is the low-power microcontroller unit 132, which serves as the module's control center, responsible for data processing and coordinating the operation of various functional units. The fifth part is the input module, which enables user interaction input functions and supports gesture sensing or pressure triggering. The sixth part is the touch screen, located directly above the first detector 12, with a symmetrical and compact layout, used to display operating status, power information, or interactive feedback.

[0070] From an overall layout perspective, the first part, the magnetic charging base, and the third part, the Hall linear sensor, are centrally symmetrically distributed around the geometric center of the outer frame 142, forming a balanced structural design. The internal space is divided into two main areas: one side is dedicated to battery placement, ensuring the stability and safety of the energy unit; the other side centrally houses other electronic components, achieving functional integration and space optimization. All electronic components are physically connected and electrically interconnected via flexible circuit boards. The conductive lines on these flexible circuit boards integrate the components into a complete circuit system through series, parallel, or hybrid connections. This not only enables power management, signal transmission, and control logic but also ensures the reliability of the module's connection under complex conditions such as bending and vibration. Ultimately, this gives the entire active ring complete capabilities for receiving, storing, controlling, interacting with, and displaying electrical energy, fulfilling its intended functions.

[0071] The following section will disclose the specific structure of the breathing valve and its connection structure with other components, in conjunction with the accompanying drawings.

[0072] For example Figure 1 As shown, the breathing valve 10 has a valve seat 101 and a valve plate 102. The valve seat 101 is a tubular structure made of aluminum alloy and has a valve channel inside. The total wall thickness of the valve seat 101 is approximately 3.2 mm. One end of the valve plate 102 is hinged to the valve seat 101. When exhaling or inhaling, the valve plate 102 is opened or closed by air pressure.

[0073] The first magnet 103 is disposed at the other end of the valve plate 102, and the second magnet 111 is fixedly disposed at the inner wall of the valve seat 101; when the breathing valve 10 is in the closed valve state, the second magnet 111 is opposite to the first magnet 103.

[0074] Since the second magnet 111 and the first magnet 103 have opposite polarities, they attract each other. Therefore, the breathing valve 10 is normally closed when not in use.

[0075] The dimensions of the epoxy resin adhesive layer 143 are designed to match the external structural features of the valve seat 101. The epoxy resin adhesive layer 143 is clearance-fitted with the valve seat 101; during user assembly, the epoxy resin adhesive layer 143 can be naturally and unobstructedly fitted onto the breather valve 10.

[0076] Example 2 like Figure 4 As shown, this embodiment provides an active detection device for a breathing trainer, which differs from Embodiment 1 in that it also includes a second detector 17.

[0077] Specifically, the second detector 17 is electrically connected to the flexible circuit board 131, and the second detector 17 is used to acquire information on airflow changes within the valve seat 101. The second detector 17 is also electrically connected to the controller 13, and the controller 13 determines the operating status of the breathing valve 10 based on the information acquired by the second detector 17.

[0078] Example 3 like Figure 5 As shown, this embodiment provides a multifunctional breathing trainer, including a breathing mask 20 and an active detection device 30 of the breathing trainer in Embodiment 1.

[0079] The support body is sleeved on the outer periphery of the breathing valve; the breathing mask is set at the air inlet end of the breathing valve, and the exhaust end of the breathing valve is provided with a funnel-shaped limiting part 21. The limiting part 21 and the breathing mask 20 cooperate with each other to prevent the support body 14 from falling off the breathing valve 10, effectively limiting the axial range of motion of the support body 14 during use, thereby fundamentally eliminating the risk of the support body 14 accidentally slipping off.

[0080] The breathing mask 20 is made of soft materials such as silicone or TPU, and is mainly used to seal the nasal cavity or oral cavity. For example, the shape of the breathing mask 20 can be selected to be close to a triangle to conform to the contour of the human nasal cavity or oral cavity. When the breathing mask 20 covers the nasal cavity, it can provide inhalation training airflow through the nose. Compared with providing inhalation training airflow through the mouth, it can better exercise the nasal muscle groups, adenoids, and open the sinus passages and exercise the inspiratory muscles.

[0081] When the user breathes, the airflow enters the breathing valve 10 and continuously drives the valve plate 102 to move.

[0082] Specifically, the first detector 12 employs a Hall linear sensor. The Hall linear sensor efficiently senses the displacement and vibration changes generated by the respiratory airflow on the first magnet 103. The Hall linear sensor thus collects multiple key physiological parameters in real time, such as the user's respiratory rate, single training session duration, and cumulative usage count, and transmits the raw signals to the controller 13. After filtering, calibrating, and performing preliminary analysis, the controller 13 synchronizes the data information in real time to the accompanying mobile terminal app or APP via a wireless communication module, allowing users and medical professionals to remotely view rehabilitation data and dynamically adjust treatment plans.

[0083] Specifically, during respiration, the airflow drives the first magnet 103 to generate high-frequency micro-amplitude vibrations. These high-frequency vibrations cause the first magnet 103 to move up and down, resulting in varying distances between it and the Hall linear sensor. Consequently, the signal strength sensed by the Hall sensor varies in strength. This mechanical motion significantly enhances the sensor's signal response strength and detection accuracy, effectively improving the real-time performance, stability, and clinical reference value of training feedback.

[0084] Due to limited space and the need to accommodate multiple functional modules, the design process must fully consider the compactness and rationality of the circuit layout, striving to maximize resource utilization and optimize the circuit structure in an extremely limited space, while also taking into account heat dissipation, anti-interference and ease of maintenance.

[0085] Circuit design such as Figure 8 As shown, to ensure signal integrity and power stability, the following measures are taken: First, battery 15 uses a miniaturized lithium battery with a rated voltage of 3.8 volts as the main power source, possessing high energy density and long cycle life. Battery 15 is connected to the main control circuit through a high-performance OVP SA8203D overvoltage protection chip to achieve real-time voltage monitoring at the input terminal. The function of this overvoltage protection chip is to quickly cut off the power supply path from the charging line to the motherboard when the input voltage exceeds a preset safety threshold due to abnormal charging or external interference, avoiding damage to the flexible circuit board or other critical components caused by transient high voltage surges, thereby significantly improving the stability and safety of the system.

[0086] Under normal operating conditions, the battery 15 continuously supplies power to the microcontroller unit 132. The microcontroller unit 132, model 2021A3, features high integration, low power consumption, and fast response, making it suitable for low-power portable devices. This microcontroller unit 132 integrates a PMU (Power Management Unit), which intelligently regulates the power distribution of each module and manages the battery 15's charging in a constant-current-constant-voltage mode using controllable charging logic, achieving automation, efficiency, and temperature monitoring during the charging process. Simultaneously, the circuit is equipped with a dedicated lithium battery protection chip, WSDF2310B. Its core function is to monitor the battery's voltage, current, and temperature in real time. Upon detecting abnormalities such as overcharging, over-discharging, overcurrent, or short circuits, it immediately cuts off the charging and discharging circuit, effectively preventing battery thermal runaway or aging, extending battery life, and ensuring safe operation. During system operation, the microcontroller unit 132 uses a low-noise LDO voltage regulator chip U7 to stabilize the battery voltage, providing a clean and stable operating voltage for the single-point touch chip RM1233AM-KD1SA, preventing accidental touches caused by power fluctuations.

[0087] When a user performs a touch operation, the input module determines the contact state by detecting minute changes in electrode capacitance and immediately sends a low-level interrupt signal to the microcontroller unit 132. Upon receiving the signal, the microcontroller unit 132 immediately starts the corresponding interrupt handling program to debounce, recognize, and logically respond to the touch event, thereby improving the sensitivity and accuracy of the interaction.

[0088] In addition, the microcontroller unit 132 also supplies power to the Hall linear sensor KTH3105 through another independent LDO voltage regulator chip U2, isolating power supply noise and ensuring its reliable operation under stable voltage. When the Hall linear sensor senses a change in the external magnetic field strength, it outputs a continuous analog signal proportional to the magnetic field strength. This signal is acquired and filtered by the built-in ADC of the microcontroller unit 132 to determine the trend of magnetic field changes, and then performs related operations such as counting, position detection, and motion direction recognition. After the microcontroller unit 132 completes the fusion processing and logical judgment of the touch signal and the Hall linear sensor signal, it drives the touch screen through the GPIO interface according to the preset algorithm, updating and displaying the processing results in real time, such as the number of Hall records, cumulative usage time, current battery level mode, or system status prompts, realizing intuitive and efficient human-computer interaction and visual feedback. The entire circuit design, while meeting the requirements of multi-functional integration, strictly controls power consumption and size, taking into account functionality, safety, and space utilization, reflecting the deep integration of high integration and intelligent control, and providing a reliable technical solution for miniaturized intelligent devices.

[0089] The Hall linear sensor and the first magnet 103 inside the breathing valve 10 form an electromagnetic induction system, which work together to achieve intelligent monitoring of the user's breathing training behavior.

[0090] When a user begins using the multi-functional breathing trainer, airflow flows steadily along the pre-set cavity inside the breathing valve 10. The dynamic action of the airflow causes the valve plate 102 to vibrate regularly. The Hall linear sensor, as a highly sensitive magnetic field detection element, can detect in real time the subtle changes in the surrounding magnetic field strength caused by the vibration of the first magnet 103.

[0091] The recognition accuracy range of Hall linear sensors is typically between ±420 Gs, with specific values ​​varying depending on the model and operating environment. When the multi-functional breathing trainer is used normally, the first magnet 103 undergoes irregular displacement in response to differences in the user's breathing rhythm, thereby causing changes in the magnetic field around the first magnet 103, such as... Figure 6 As shown, the magnetic induction intensity generated by the first magnet 103 itself varies with distance, ranging from approximately 0 Gs to 921 Gs. The closer the distance to the first magnet 103, the stronger the magnetic field intensity can be sensed by the Hall linear sensor. The valve plate 102 is initially horizontal, denoted as 0°. The limiting state is the maximum rotation angle of the valve plate 102. That is, the movement amplitude of the first magnet 103 of the multifunctional inhalation trainer is the angle difference between the limiting state and the initial state, and the angle difference is 8°. The total wall thickness of the valve seat 101 is approximately 3.2 mm. In the initial state, the straight-line distance between the first magnet 103 and the outer diameter of the multi-functional breathing trainer is 8.2 mm. In the extreme state, the straight-line distance between the first magnet 103 and the outer diameter of the multi-functional breathing trainer is approximately 3 mm. Since the straight-line distance between the multi-functional breathing trainer and its outer diameter is 5.5-8 mm when the multi-functional breathing trainer is in use, the magnetic field strength emitted by the first magnet 103 is 33 GS to 76 GS. When the Hall linear sensor detects the analog signal emitted by the magnetic field of the multi-functional breathing trainer, it identifies the value on the Hall linear sensor. The value on the Hall linear sensor varies depending on the degree of exhalation of the user, so the values ​​may be divided into m1, m2, m3, m4, m5, m6, etc., in order of magnitude, and there may even be values ​​lower than m1 and values ​​larger than m7.

[0092] like Figure 7 As shown, the values ​​of the analog signal from the Hall linear sensor are taken as a lower value and a higher value, with the lower value being m. a The higher value is m bWhen the multi-functional breathing trainer is used in a simulated manner, under static conditions, the Hall linear sensor will identify a simulated signal value a1; under light touch conditions, the Hall linear sensor will identify a simulated signal value a2; under gentle use conditions, the Hall linear sensor will identify a simulated signal value a3; under normal use conditions, the Hall linear sensor will identify a simulated signal value a4; and under vigorous use conditions, the Hall linear sensor will identify a simulated signal value a5; where a5 > a4 > a3 > m. b >m a Since a2 > a1, the value of the analog signal detected by the Hall linear sensor will decrease from below m within one usage cycle. a , to above m b This process, which is unique within a usage cycle, is when the multi-functional inhalation trainer is set to be used; when the value of the analog signal detected by the Hall linear sensor changes from above m within a usage cycle. b to below m a This process is unique within a single usage cycle, meaning it is set to end when the multi-functional breathing trainer is no longer in use.

[0093] Preferred, m a The value is 190-220, m b The value is 290-320.

[0094] More preferably, m a The value is 200-220, m b The value is 300-320.

[0095] The optimal choice, m a The value is 205, m b The value is 304.

[0096] The analog signal detected by the Hall linear sensor is converted into a digital signal and transmitted to the touch screen. The touch screen is controlled by software to start timing from 0 minutes and 0 seconds. After the timing starts, since the entire breathing process is divided into exhalation and inhalation, the multi-functional breathing trainer generates air pressure during exhalation, which can be detected by the Hall linear sensor. However, no signal is generated during inhalation. Therefore, through testing, the breathing process lasts about 0-10 seconds. This embodiment uses a 5-second detection method to detect whether the multi-functional breathing trainer is being used. If it is detected in this 5-second cycle, the time continues to increase by 5 seconds. The more macroscopic time intervals are 0, 1, 2, 3, 4, and 5 seconds. If it is detected in any of these 5 seconds, then 5 seconds are added to this second. The total time T is as follows: T = t × (n + 1), where n is a natural number; t is a breathing cycle in seconds, t = 5 ± 2 s.

[0097] Because the recognition accuracy of Hall linear sensors inherently fluctuates, their sensitivity is dynamically adjusted within the nominal range due to factors such as temperature, power supply stability, and external electromagnetic interference. Simultaneously, the magnetic induction changes generated by the multi-functional breathing trainer during actual use are not constant but fluctuate in real time with the user's breathing force, frequency, and the precision of their movements, falling precisely within the accuracy range recognizable by the Hall linear sensor. When the magnetic induction intensity value generated by the trainer at a certain moment effectively matches the current recognition sensitivity range of the Hall linear sensor, the sensor immediately senses this weak but distinctive magnetic signal change. This signal is then stably captured and converted into a continuous analog electrical signal, transmitted to the microcontroller unit 132. Upon receiving the signal, the microcontroller unit 132 first performs filtering and amplification to eliminate noise interference, and then accurately converts the analog electrical signal into a digital signal through its built-in analog-to-digital converter module. Finally, the respiratory parameters, such as respiratory rate and depth trend, after algorithm calibration and unit conversion, are displayed in real time on the device's touch screen, providing feedback to the user in the form of intuitive numbers or waveforms. This enables dynamic monitoring and data visualization of the breathing training process, helping users to scientifically adjust their training rhythm and improve their user experience and training results.

[0098] This embodiment provides a multifunctional breathing trainer with a standard mode and an energy-saving mode, and the working logic is shown in the table below.

[0099] Table 1 Table 2 Furthermore, the Hall linear sensor can employ a phased activation mechanism. This design is primarily based on in-depth analysis of users' daily routines and habits when using the multi-functional breathing trainer, aiming to achieve more efficient and intelligent energy management. Considering that most users typically wake up around 8:00 AM and then spend about half an hour completing morning preparations such as washing up, the system sets the training start time to 8:30 AM and continues until 12:30 PM, covering a critical five-hour usage period. To optimize energy consumption, the system divides these five hours into five independent time intervals. Within each interval, the Hall linear sensor activates as needed and performs status sensing, rather than operating continuously. This segmented sensing strategy effectively reduces the device's continuous operating time, significantly lowers overall power consumption, and avoids energy waste. Simultaneously, while ensuring functional integrity, it greatly alleviates module overheating and aging issues, thereby extending the actual lifespan of the active ring. Under limited space and power capacity, this solution achieves a good balance between low power consumption and high response through refined time management and inductive scheduling, significantly improving the system's energy efficiency ratio and ultimately achieving the practical goal of long-lasting active loop power supply, bringing users a more stable and longer-lasting user experience.

[0100] Example 4 This embodiment provides a multifunctional breathing trainer, which differs from Embodiment 3 in that the first detector 12 uses a triaxial accelerometer.

[0101] The triaxial accelerometer not only has higher sensitivity and a wider dynamic response range, but it can also simultaneously acquire acceleration information in three orthogonal directions, thereby comprehensively capturing the minute vibrations caused by airflow during equipment use.

[0102] When a user performs breathing training, the airflow inside the multi-functional breathing trainer generates mechanical vibrations with specific frequencies and irregular amplitudes. These vibration signals are captured in real time by a triaxial accelerometer, and signal processing algorithms such as filtering and spectrum analysis can be used to extract the dominant frequency, amplitude variation trend, and periodic characteristics of the vibrations. Based on this data, the system can further calculate key parameters such as single-use duration, usage frequency, breathing rhythm cycle, and training intensity distribution. Combined with timestamp information, a long-term user behavior model can be established to analyze training patterns, compliance, and habit changes.

[0103] Furthermore, the high sampling rate and low noise characteristics of the triaxial accelerometer enable the recognition of even subtle user actions, helping to distinguish between effective training and accidental touches, thus improving data accuracy. Continuous accumulation and analysis of this sensor data can also provide strong support for personalized training program recommendations, user feedback prompts, and equipment maintenance warnings, significantly enhancing the product's intelligence level and user experience. Compared to Hall effect linear sensors, the triaxial accelerometer not only exhibits significant advantages in power consumption, with lower energy consumption suitable for long-term stable operation, but also achieves a substantial improvement in recognition accuracy, enabling it to more sensitively and accurately capture subtle changes in spatial motion. Simultaneously, its overall structure is more compact, with a smaller physical volume, facilitating integration into precision equipment without occupying excessive space. This characteristic allows for more rational spatial layout and more efficient energy distribution when applied to active loops, effectively extending the module's continuous operating time. Moreover, due to its multi-dimensional acceleration detection capabilities, the system response is more sensitive, data feedback is more stable, and the overall device structure design is therefore more compact, lightweight, and refined, improving product reliability and user experience.

[0104] Example 5 like Figure 4 As shown, this embodiment provides a multifunctional breathing trainer, including a breathing mask 20 and an active detection device for the breathing trainer in embodiment 2, and the second detector 17 is a gas flow sensor.

[0105] The support body 14 is sleeved on the outer periphery of the breathing valve; the exhaust end of the breathing valve is provided with a funnel-shaped limiting part 21, which cooperates with the breathing mask 20 to prevent the support body 14 from falling off the breathing valve 10.

[0106] Gas flow sensors enable more accurate and comprehensive real-time monitoring of the usage status of multi-functional breathing trainers.

[0107] The gas flow sensor can highly sensitively capture subtle changes in airflow during breathing, possessing excellent accuracy and dynamic response capabilities. When the device is stationary or in handheld standby mode, the internal airflow is extremely weak, and the sensor output is a stable low value; however, once the user begins breathing training, the inhaled or exhaled airflow quickly triggers the sensor response, generating a clear and identifiable signal, thereby accurately determining whether the device is actually being used.

[0108] Gas flow sensors not only boast advantages such as small size and easy integration into compact portable devices, but also feature fast response, high detection accuracy, good repeatability, and low power consumption, making them ideal for long-term continuous operation. Furthermore, they exhibit excellent environmental adaptability and strong anti-interference capabilities, remaining unaffected by external vibrations, tilting, or hand-held shaking, fundamentally reducing the probability of false positives and false negatives, and significantly improving the reliability, stability, and user experience of the overall monitoring system. In addition, the gas flow sensor's output signal linearity facilitates subsequent signal processing and algorithm analysis, providing high-quality, continuous data support for breathing pattern recognition, usage frequency statistics, training effect evaluation, and personalized feedback suggestions, powerfully promoting the intelligent and scientific development of breathing training.

[0109] Example 6 This embodiment provides a multifunctional inhalation trainer, which differs from Embodiment 3 in that it has two first detectors, namely a Hall linear sensor and a triaxial accelerometer.

[0110] This embodiment integrates the Hall linear sensor with the newly added triaxial accelerometer to build a more intelligent and efficient working logic system.

[0111] Specifically, this embodiment integrates a triaxial accelerometer based on embodiment 3, and the triaxial accelerometer is electrically connected to the flexible circuit board. The triaxial accelerometer and the original Hall linear sensor form a complementary cooperation mechanism. When the triaxial accelerometer detects displacement of the active loop in real time, such as when it is picked up by the user, the system determines that it is activated, starts the Hall linear sensor, puts the Hall linear sensor into working state, and begins to collect magnetic field change signals. At the same time, the triaxial accelerometer enters a low-power sleep mode to save energy. At this time, the microcontroller unit will prioritize responding to and processing the detection data from the Hall linear sensor to ensure the continuity and accuracy of position or state recognition. When the Hall linear sensor cannot recognize a valid signal due to environmental interference or leaving the sensing area, or when there is no new input for a period of time, the microcontroller unit will automatically wake up the triaxial accelerometer in sleep mode and re-detect the motion state of the module. If the triaxial accelerometer senses that it has been placed, is stationary, or has been placed, the microcontroller unit determines that the use is over and controls the entire device to enter a low-power sleep state, thereby realizing a closed-loop control logic of automatic wake-up and automatic sleep.

[0112] This design not only enhances the intelligence level of the device, but also effectively optimizes power consumption management and improves ease of use and stability.

[0113] The overall size design of the active detection device in a breathing trainer needs to comprehensively consider the spatial layout and functional compatibility of its internal components. A key factor is the size and shape of the core components, especially the battery—the largest component in the module, with a thickness of approximately 1.8mm, a width of approximately 7mm, and an outer surface circumference of approximately 32mm. It has an overall arc-shaped structure, with positive and negative contacts integrated at both ends for connecting to the circuit system. Therefore, the battery's geometric parameters directly determine the minimum feasible size of the active ring. In the preliminary design, the active ring was designed to match the battery's size and shape with the external structural features of the multi-functional breathing trainer, ultimately determining a ring-shaped structure with an inner diameter of approximately 26.5mm, a thickness of approximately 2.7mm, and a width of approximately 8mm. This design aims to allow the support to be magnetically fixed to the outer surface of the breathing valve. That is, when the inner diameter of the active ring (26.5mm) is larger than the outer diameter of the breathing valve (26.4mm), the support can naturally and unobstructedly fit into the breathing valve during user assembly, achieving convenient installation and charging connection.

[0114] However, actual assembly tests revealed that the above dimensions were not the optimal solution. After testing, the following preferred assembly solutions were found: Preferred Solution 1: Because the internal magnetic charging base has a planar structure and its height slightly exceeds the inner diameter edge of the support body (0.1-0.2mm), it generates significant frictional resistance between the support body and the breathing valve surface during assembly. This weakens the magnetic attraction force, causing the magnetic positioning function to fail, making it difficult for the user to perceive whether it is properly installed. To solve this problem, the inner diameter of the support body is optimized and adjusted. While ensuring no mechanical interference with the magnetic charging base and the breathing valve body, the inner diameter of the support body is increased to 26.6-26.7mm. This additional inner diameter range (0.1-0.2mm) is used to increase the magnetic attraction distance.

[0115] Preferred Option 2: By utilizing the flexibility of the flexible circuit board, while keeping the inner diameter of the existing support unchanged, the height of the magnetic charging base can be reduced by 0.1-0.2mm towards the inside of the active ring, without affecting the magnetic attraction effect. In other words, through the process, the friction between the inner diameter surface of the support and the outer diameter surface of the breathing valve is reduced.

[0116] Preferred Option 3: As seen from the above preferred options 1 and 2, the positioning effect of the magnetic charging base and the fixed magnet depends on the distance between the magnetic charging base and the second magnet. Therefore, the hole for fixing the fixed magnet on the valve seat of the breathing valve can be opened. For example... Figure 9As shown, the second magnet 111 is embedded in the valve seat 101. This design minimizes the distance between the second magnet 111 and the magnetic charging base, sometimes separated only by an aluminum alloy shell. This significantly enhances the interaction force between the second magnet 111 and the magnetic charging base. Alternatively, in some embodiments, holes can be made in the corresponding positions of the aluminum alloy shell to install the second magnet between the aluminum alloy shell and the magnetic charging base, further maximizing the interaction force between them. These three improvements not only effectively reduce assembly friction but also significantly enhance the clarity and stability of the magnetic response, allowing users to perceive a noticeable magnetic effect upon contact. This provides a direct indication that the active ring has been correctly aligned and installed, improving the product's ease of use and user experience.

[0117] Example 7 like Figure 10 As shown, this embodiment provides a multifunctional breathing trainer, which differs from embodiment 3 in that the breathing mask 20 is located at the exhaust end of the breathing valve, and this embodiment does not have a flared limiting part.

[0118] The entire breathing process is divided into exhalation and inhalation. During inhalation, the multi-functional breathing trainer generates air pressure, which can be recognized by the Hall linear sensor. However, no signal is generated during exhalation.

[0119] Although embodiments of this application have been shown and described above, the scope of protection of this invention is not limited thereto. Any variations or substitutions that can be conceived without inventive effort should be covered within the scope of protection of this invention. Unless expressly stated otherwise, no element, action or instruction used herein should be construed as critical or necessary.

Claims

1. An active detection device for a breathing trainer, characterized in that, include: At least one first detector is used to acquire information on magnetic field changes and / or vibration information of the breathing trainer; as well as The controller is configured to be electrically connected to the at least one first detector; The controller calculates the breathing frequency and / or single continuous running duration and / or cumulative number of uses of the breathing trainer based on the information obtained by the at least one first detector.

2. The active detection device for a breathing trainer according to claim 1, characterized in that, Also includes: A storage battery is used to power the controller and the first detector; as well as A wireless communication module for communicating with at least one terminal; The controller transmits the calculated information to at least one terminal via the wireless communication module. The controller includes: Flexible circuit boards; and A microcontroller unit is configured to be electrically connected to the flexible circuit board; Both the first detector and the battery are configured to be electrically connected to the flexible circuit board.

3. The active detection device for a breathing trainer according to claim 2, characterized in that, Also includes: The input module is used to generate and send control commands to the controller; as well as An output module, at least for displaying the calculation results of the controller; The controller, according to the control command, at least controls itself to shut down or turn on.

4. The active detection device for a breathing trainer according to claim 3, characterized in that, The first detector includes a Hall linear sensor and / or a triaxial accelerometer.

5. The active detection device for a breathing trainer according to claim 3, characterized in that, Also includes: At least one second detector is used to acquire information on airflow changes within the breathing trainer; The at least one second detector is configured to be electrically connected to the controller, and the controller determines the working status of the breathing valve based on the information obtained by the at least one second detector.

6. A multifunctional breathing trainer, comprising a breathing valve, characterized in that, It also includes an active detection device for the breathing trainer as described in any one of claims 3-5; The breathing valve has a valve seat and a valve plate, which are movably connected, and a first magnet is provided on the valve plate.

7. The active detection device for a breathing trainer according to claim 6, characterized in that, Also includes: A support structure is provided to support the first detector and the controller; The support body is provided with a magnetic attraction component, and a second magnet is fixedly provided inside the valve seat; The second magnet has the opposite polarity to the magnetic attraction component, and the support is magnetically connected to the outside of the valve seat through the magnetic attraction component and the second magnet; The first magnet has opposite polarities to the second magnet.

8. The active detection device for a breathing trainer according to claim 7, characterized in that, The magnetic component is a magnetic charging base, which is used to receive charging current to charge the battery.

9. A multifunctional inhalation trainer according to claim 7, characterized in that: A breathing mask is provided at the air inlet end of the breathing valve; The support body is arranged in a ring shape and is sleeved on the outer periphery of the breathing valve; The exhaust end of the breathing valve is provided with a funnel-shaped limiting part, which cooperates with the breathing mask to prevent the support from falling off the breathing valve.

10. A method for identifying a multifunctional inhalation trainer as described in any one of claims 6-9, characterized in that, Includes the following steps: 1) Take a lower value and a higher value from the analog signal of the first detector. The lower value is... The higher value ; Under static conditions, the first detector will identify the value of an analog signal. ; When the multi-functional breathing trainer is lightly touched, the first detector will recognize a value of an analog signal. ; Under conditions of subtle use, the first detector will identify a value of an analog signal. ; When the multi-functional breathing trainer is used normally, the first detector will identify a value of an analog signal. ; Under conditions where the multi-functional breathing trainer is used extensively, the first detector will identify a value of an analog signal. Among them, it is set as ; 2) The value of the analog signal detected by the first detector is reduced from below a certain value within one usage cycle. to higher This process is unique within a single usage cycle. The controller detects that the multi-functional breathing trainer is being used. When the value of the analog signal detected by the first detector increases from higher than [value] within a usage cycle to below This process is unique within a single usage cycle, and the controller determines that the multi-functional inhalation trainer has reached the end of its use. Since the entire breathing process is divided into exhalation and inhalation, the multi-functional breathing trainer generates air pressure during exhalation, which can be detected by the first detector. However, no signal is generated during inhalation. The controller uses a periodic detection method to check whether the multi-functional breathing trainer is being used. If it is detected within a set period, the controller adds another period to the time. If it is detected at any second within the period, the controller adds another period to the total time. The relationship is as follows: , For natural numbers, One respiratory cycle is one breath cycle.

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