A portable deep breathing incentive trainer for respiratory rehabilitation

Abstract

This invention discloses a portable deep breathing stimulation trainer for respiratory rehabilitation, relating to the field of medical device technology. It includes a breathing tubing with an auxiliary tube fixedly connected to its bottom surface, and a diaphragm fixedly connected to the inner wall of the auxiliary tube. This portable deep breathing stimulation trainer for respiratory rehabilitation, through the arrangement of the auxiliary tube, diaphragm, and receiver, diverts inspiratory airflow from the breathing tubing into the auxiliary tube to directly impact the diaphragm, generating regular vibrations. The receiver collects these vibration signals in real time and converts them into electrical signals, transmitting them to the controller. This detection method eliminates the need for any throttling or resistance elements in the main airflow channel, thus achieving accurate detection of inspiratory flow rate without increasing the patient's inspiratory resistance burden, ensuring a smooth and natural training process. It solves the technical problem of traditional flow sensors affecting the patient's normal respiratory rhythm due to the addition of resistance components.

Description

Technical Field

[0001] This invention relates to the field of medical device technology, specifically to a portable deep breathing stimulation trainer for respiratory rehabilitation. Background Technology

[0002] Respiratory rehabilitation training is an important intervention in the comprehensive treatment of patients with chronic obstructive pulmonary disease, post-thoracic and abdominal surgery, and respiratory muscle dysfunction. It aims to improve pulmonary ventilation and respiratory muscle endurance through regular deep breathing exercises. Existing respiratory trainers are mainly divided into two categories: mechanical impedance type and electronic sensor type. The former relies on throttling elements or spring valves to apply resistance loads in the inspiratory path to achieve the training effect, while the latter integrates differential pressure or turbine flow sensors in the airflow channel to achieve real-time quantitative monitoring of respiratory parameters. With the development of electronic technology, intelligent respiratory training devices with real-time feedback functions are gradually becoming more widespread. These devices collect parameters such as inspiratory flow rate through sensors, which are then processed by a processor to provide patients with intuitive motivational signals during training.

[0003] However, the existing devices described above all place the sensor or resistance element directly within the main airflow channel of the patient's inspiration when detecting inspiratory flow. Differential pressure sensors rely on the pressure drop generated by the throttling element to calculate the flow rate, while turbine sensors rely on airflow to drive rotating components. Both inevitably constitute additional resistance sources within the main channel. Patients must overcome this resistance to complete the inspiratory action. For rehabilitation patients whose respiratory muscle strength is already weakened, this additional resistance easily induces compensatory shallow and rapid breathing patterns, causing involuntary changes in respiratory rhythm and inspiratory amplitude. This deviates from the stable, deep, and long requirements of physiological deep breathing, resulting in the collected flow parameters failing to accurately reflect the patient's natural breathing capacity under undisturbed conditions. Training feedback also becomes inaccurate, thus requiring improvement. Summary of the Invention

[0004] The purpose of this invention is to provide a portable deep breathing stimulation trainer for respiratory rehabilitation, in order to solve the problem in the prior art that the flow detection element is placed in the main airflow channel, which creates additional resistance to the patient's inhalation, resulting in interference with the respiratory rhythm and inaccurate training feedback.

[0005] To achieve the above objectives, the present invention provides the following technical solution: a portable deep breathing stimulation trainer for respiratory rehabilitation, comprising a breathing tube, wherein an auxiliary tube is fixedly connected to the bottom surface of the breathing tube, and a diaphragm is fixedly connected to the inner wall of the auxiliary tube.

[0006] A mounting clip is fixedly connected to the top surface of the breathing tube. A fixed frame is rotatably connected to the inner wall of the mounting clip. Multiple indicator lights are fixedly connected to the surface of the fixed frame. A receiver is fixedly connected to the inner wall of the fixed frame. A controller body is electrically connected to the top of the receiver. A circuit board is electrically connected to the top of the controller body, and the circuit board is electrically connected to the indicator lights. A battery is electrically connected to the top of the circuit board.

[0007] Furthermore, a insertion hole is provided at the top of the surface of the breathing tube, a connecting frame is inserted into the top of the insertion hole, and a pull rod is fixedly connected to the top of the connecting frame.

[0008] Furthermore, a coarse filter screen is fixedly connected to one side of the inner wall of the connecting frame, and a fine filter screen is fixedly connected to the other side of the inner wall of the connecting frame.

[0009] Furthermore, a limiting groove is provided on both sides of one end of the breathing tube, and a positioning groove is provided on the inner wall of the limiting groove.

[0010] Furthermore, a positioning block is inserted into the inner wall of the limiting slot, and the front end of the positioning block is rotated and inserted into the positioning slot.

[0011] Furthermore, an air suction pipe is fixedly connected to one side of the positioning block.

[0012] Furthermore, the controller body is preset with a respiratory rate threshold and an inspiratory flow rate threshold. The controller body is used to calculate the actual respiratory rate and the actual inspiratory flow rate based on the diaphragm vibration signal received by the receiver, and compare the actual respiratory rate with the respiratory rate threshold and the actual inspiratory flow rate with the inspiratory flow rate threshold. When the actual respiratory rate is within the respiratory rate threshold range and the actual inspiratory flow rate reaches the inspiratory flow rate threshold, the controller body controls the circuit board to drive the indicator light to illuminate to indicate the correct breathing state.

[0013] Furthermore, the indicator light includes multiple groups of LED lights of different colors. The controller body is also used to control the LED lights of different colors to light up according to the deviation of the actual respiratory rate from the respiratory rate threshold and the deviation of the actual inspiratory flow rate from the inspiratory flow rate threshold, so as to form a graded excitation indication signal. The controller body is also equipped with a timing module to record the duration of a single effective breath, and to control the indicator light to flash at a preset frequency when the duration reaches the preset effective duration.

[0014] Furthermore, the controller body is also equipped with a wireless communication module. The wireless communication module is used to transmit the diaphragm vibration signal, actual respiratory rate data, actual inspiratory flow data and indicator light illumination record data received by the receiver to an external smart terminal via Bluetooth or Wi-Fi protocol. The controller body is also used to adjust the respiratory rate threshold and inspiratory flow threshold according to the training parameters sent by the external smart terminal.

[0015] Furthermore, the output terminal of the battery is electrically connected to the power input terminal of the circuit board. The circuit board is equipped with a power management module, which is used to detect the remaining power of the battery and control the indicator light to light up in a low power warning mode when the remaining power is lower than a preset power threshold.

[0016] Compared with existing technologies, the present invention provides a portable deep breathing stimulation trainer for respiratory rehabilitation. Through the arrangement of an auxiliary tube, diaphragm, and receiver, the inspiratory airflow in the breathing tube is diverted to the auxiliary tube to directly impact the diaphragm and generate regular vibrations. The receiver collects the vibration signal in real time and converts it into an electrical signal, which is then transmitted to the controller. This detection method does not require any throttling or resistance elements in the main airflow channel, thus achieving accurate detection of inspiratory flow rate without increasing the patient's inspiratory resistance burden. This ensures a smooth and natural training process and solves the technical problem that traditional flow sensors affect the patient's normal breathing rhythm due to the addition of resistance components. It also provides a real and reliable raw data foundation for subsequent intelligent judgment.

[0017] By setting preset respiratory rate and inspiratory flow thresholds within the controller body, and dynamically comparing the actual respiratory rate and inspiratory flow calculated in real time with the two thresholds, the controller body determines a valid deep breath and activates the indicator light only when both parameters meet the standards. This establishes a strict standard-setting mechanism in both frequency and flow dimensions, effectively eliminating the possibility of ineffective breathing patterns such as shallow and rapid breathing or explosive inhalation being misjudged as effective training. This ensures that each visual stimulus signal corresponds to a genuine deep breathing action with alveolar ventilation and respiratory muscle training value, significantly improving the accuracy and scientific nature of respiratory rehabilitation training feedback.

[0018] The controller's built-in wireless communication module transmits the collected diaphragm vibration signals, actual respiratory rate data, actual inspiratory flow data, and indicator light illumination data to an external smart terminal in real time. Combined with training parameters sent from the external smart terminal, the controller can remotely and dynamically adjust the respiratory rate and inspiratory flow thresholds within the controller. This enables personalized remote configuration of training programs and centralized tracking and management of training data. Medical staff can flexibly adjust training intensity parameters based on the patient's lung function recovery at different stages of rehabilitation, allowing for updates and iterations of training prescriptions without requiring the patient to return to the hospital. This significantly expands the applicability and continuity of the trainer throughout the entire rehabilitation cycle. Attached Figure Description

[0019] To more clearly illustrate the technical solutions in the embodiments of this application or the prior art, the drawings used in the embodiments will be briefly introduced below. Obviously, the drawings described below are only some embodiments recorded in this invention. For those skilled in the art, other drawings can be obtained based on these drawings.

[0020] Figure 1 This is a schematic diagram of the overall structure provided in an embodiment of the present invention;

[0021] Figure 2 This is a schematic diagram of the positioning block structure provided in an embodiment of the present invention;

[0022] Figure 3 This is a schematic diagram of the coarse filter structure provided in an embodiment of the present invention;

[0023] Figure 4 This is a schematic diagram of the connecting frame structure provided in an embodiment of the present invention;

[0024] Figure 5 A schematic diagram of the auxiliary pipeline structure provided in an embodiment of the present invention;

[0025] Figure 6 This is a schematic diagram of the main structure of the controller provided in an embodiment of the present invention.

[0026] Explanation of reference numerals in the attached figures:

[0027] 1. Breathing tubing; 2. Auxiliary tubing; 3. Diaphragm; 4. Mounting clamp; 5. Fixing frame; 6. Indicator light; 7. Receiver; 8. Controller body; 9. Circuit board; 10. Battery; 11. Plug hole; 12. Connecting frame; 13. Pull rod; 14. Coarse filter; 15. Fine filter; 16. Limiting slot; 17. Positioning block; 18. Inhalation tube. Detailed Implementation

[0028] To enable those skilled in the art to better understand the technical solution of the present invention, the present invention will be further described in detail below with reference to the accompanying drawings.

[0029] As attached Figure 1 To be continued Figure 6 As shown:

[0030] Example 1:

[0031] The present invention provides a portable deep breathing stimulation trainer for respiratory rehabilitation, including a breathing tube 1, an auxiliary tube 2 fixedly connected to the bottom surface of the breathing tube 1, and a diaphragm 3 fixedly connected to the inner wall of the auxiliary tube 2.

[0032] A mounting clip 4 is fixedly connected to the top surface of the breathing tube 1. A fixing frame 5 is rotatably connected to the inner wall of the mounting clip 4. Multiple indicator lights 6 are fixedly connected to the surface of the fixing frame 5. A receiver 7 is fixedly connected to the inner wall of the fixing frame 5. A controller body 8 is electrically connected to the top of the receiver 7. A circuit board 9 is electrically connected to the top of the controller body 8. The circuit board 9 is electrically connected to the indicator lights 6. A battery 10 is electrically connected to the top of the circuit board 9.

[0033] The controller body 8 has preset respiratory rate thresholds and inspiratory flow rate thresholds. The controller body 8 is used to calculate the actual respiratory rate and actual inspiratory flow rate based on the vibration signal of the diaphragm 3 received by the receiver 7, and compare the actual respiratory rate with the respiratory rate threshold and the actual inspiratory flow rate with the inspiratory flow rate threshold. When the actual respiratory rate is within the respiratory rate threshold range and the actual inspiratory flow rate reaches the inspiratory flow rate threshold, the controller body 8 controls the circuit board 9 to drive the indicator light 6 to light up to indicate the correct breathing state.

[0034] Indicator 6 includes multiple groups of LEDs of different colors. The controller body 8 is also used to control the LED groups of different colors to light up according to the deviation of the actual respiratory rate from the respiratory rate threshold and the deviation of the actual inspiratory flow rate from the inspiratory flow rate threshold, so as to form a graded excitation indication signal. The controller body 8 is also equipped with a timing module to record the duration of a single effective breath and control indicator 6 to flash at a preset frequency when the duration reaches the preset effective duration.

[0035] The controller body 8 is also equipped with a wireless communication module. The wireless communication module is used to transmit the vibration signal of the diaphragm 3, the actual respiratory rate data, the actual inspiratory flow data and the data recorded by the indicator light 6 received by the receiver 7 to an external smart terminal via Bluetooth or Wi-Fi protocol. The controller body 8 is also used to adjust the respiratory rate threshold and inspiratory flow threshold according to the training parameters sent by the external smart terminal.

[0036] The output terminal of the storage battery 10 is electrically connected to the power input terminal of the circuit board 9. The circuit board 9 is equipped with a power management module, which is used to detect the remaining power of the storage battery 10 and control the indicator light 6 to light up in a low power warning mode when the remaining power is lower than a preset power threshold.

[0037] During use, airflow enters through breathing tube 1 and is diverted to auxiliary tube 2. The airflow impacts and causes a diaphragm 3 fixedly connected to the inner wall of auxiliary tube 2 to vibrate regularly. The vibration frequency and amplitude of the diaphragm 3 change in real time according to the user's actual inspiratory flow rate and respiratory rhythm. The vibration signal of the diaphragm 3 is collected and converted in real time by a receiver 7 fixedly connected to the inner wall of the fixed frame 5. The receiver 7 converts the collected analog vibration signal into an electrical signal and transmits it to the controller body 8. The controller body 8 has preset respiratory frequency thresholds and inspiratory flow rate thresholds. Based on the vibration signal of the diaphragm 3 transmitted by the receiver 7, it performs algorithmic calculations to determine the user's current actual respiratory frequency and actual inspiratory flow rate. It compares the actual respiratory frequency with the preset respiratory frequency threshold and the actual inspiratory flow rate with the preset inspiratory flow rate threshold. When the actual respiratory frequency is within the respiratory frequency threshold range and the actual inspiratory flow rate reaches the inspiratory flow rate threshold, the controller body 8 determines that the current respiratory frequency is within the respiratory frequency threshold range and the actual inspiratory flow rate reaches the inspiratory flow rate threshold. When the inhalation state is an effective deep breathing state, a drive signal is output through the circuit board 9 electrically connected to its top, controlling the illumination of multiple indicator lights 6 fixedly connected to the surface of the fixed frame 5, providing the user with immediate positive visual feedback and incentive indications. At the same time, through the fixed connection between the mounting clip 4 and the top surface of the breathing tube 1, and the rotational connection between the inner wall of the mounting clip 4 and the fixed frame 5, the user can flexibly adjust the orientation of the fixed frame 5 according to their own usage habits or observation angle, so that the illumination state of the indicator lights 6 can be presented in the user's field of vision at the best angle. Throughout the training process, the battery 10 electrically connected to the top of the circuit board 9 provides continuous and stable working power to the receiver 7, the controller body 8, the circuit board 9, and the indicator lights 6, ensuring that all electronic components operate normally under portable conditions without external power supply, thereby realizing real-time monitoring, intelligent judgment, graded incentives, and portable power supply for the entire deep breathing training process, effectively guiding the user to conduct standardized respiratory rehabilitation training.

[0038] Example 2:

[0039] This embodiment is basically the same as the previous embodiment, except that the top surface of the breathing tube 1 is provided with a plug hole 11, a connecting frame 12 is inserted into the top of the plug hole 11, a pull rod 13 is fixedly connected to the top of the connecting frame 12, a coarse filter 14 is fixedly connected to one side of the inner wall of the connecting frame 12, a fine filter 15 is fixedly connected to the other side of the inner wall of the connecting frame 12, a limiting slot 16 is provided on both sides of one end of the breathing tube 1, a positioning groove is provided on the inner wall of the limiting slot 16, a positioning block 17 is inserted into the inner wall of the limiting slot 16, and the front end of the positioning block 17 is inserted into the positioning groove after rotation, and an inhalation tube 18 is fixedly connected to one side of the positioning block 17.

[0040] In use, the user can pull the connecting frame 12 upwards from the insertion hole 11 at the top of the surface of the breathing tube 1 by holding the pull rod 13, according to training needs or cleaning and maintenance requirements. The coarse filter 14 fixedly connected to one side of the inner wall of the connecting frame 12 can initially intercept the external air entering the breathing tube 1, filtering out large particles of dust or foreign objects. The fine filter 15 fixedly connected to the other side of the inner wall of the connecting frame 12 performs secondary fine filtration on the airflow after coarse filtration, effectively removing small particles and some bacteria. The two work together to form a dual filtration system to ensure the cleanliness of the air inhaled by the user and reduce the risk of respiratory tract infection. At the same time, the user can insert the disposable or replaceable inhalation tube 18 into the limiting slots 16 opened on both sides of one end of the breathing tube 1 through the positioning block 17 fixedly connected to one side, and let the front end of the positioning block 17 slide along the inner wall of the limiting slot 16. After being inserted into place, rotate it at a certain angle so that the front end of the positioning block 17 is engaged in the positioning groove opened in the inner wall of the limiting groove 16, thereby realizing the quick insertion and reliable locking of the inhalation tube 18 and the breathing tube 1, preventing it from loosening during use; when it is necessary to replace the inhalation tube 18 with a different specification or to disinfect and clean the inhalation tube 18, the user can rotate the positioning block 17 in the opposite direction to disengage its front end from the positioning groove, and then pull the positioning block 17 out of the limiting groove 16, so that the inhalation tube 18 can be easily disassembled. The connecting frame 12 and the coarse filter 14 and fine filter 15 inside can also be taken out as a whole from the insertion hole 11 with the help of the pull rod 13, which is convenient for regular cleaning or replacement of filter materials to maintain the filtration effect and smooth ventilation; the entire assembly and disassembly process does not require additional tools, is easy to operate, and fully adapts to the hygiene requirements and personalized adaptation needs of portable respiratory rehabilitation trainers in different usage environments.

[0041] Application example:

[0042] This device is suitable for patients with decreased lung function due to chronic obstructive pulmonary disease, post-pneumonia, limited lung expansion after thoracic or abdominal surgery, respiratory muscle weakness, or prolonged bed rest. It enables individualized and standardized deep breathing training in diverse settings such as clinical rehabilitation, respiratory medicine, home care, and community healthcare. This patient group typically exhibits shallow and rapid breathing patterns, insufficient inspiratory flow, decreased respiratory muscle endurance, and poor compliance due to a lack of self-directed training feedback. Traditional training methods often rely on verbal instruction from medical staff or simple blowing devices, making it difficult to objectively quantify and assess training quality and provide real-time motivation and guidance, resulting in inconsistent rehabilitation outcomes. This invention combines respiratory airflow detection with graded photoelectric feedback technology, using a portable handheld structure as a carrier, enabling patients to perform precise deep breathing stimulation training in any position and environment. During the training process, inspiratory flow and respiratory rate are monitored in real time by built-in sensors and dynamically compared with preset standards. The training achievement status is intuitively presented through a multi-color indicator light group, thereby transforming abstract respiratory parameters into visually perceptible stimulation signals. This helps patients establish correct respiratory perception and rhythm control capabilities. At the same time, the training data is synchronized to an external smart terminal through wireless data transmission, facilitating medical staff to remotely track training progress and dynamically adjust training prescriptions, effectively improving the accuracy, compliance, and continuity of respiratory rehabilitation training.

[0043] First, medical staff set training parameters on an external smart terminal based on the patient's basic pulmonary function assessment results and rehabilitation goals. These parameters include inspiratory flow rate thresholds and respiratory rate threshold ranges. The parameters are then transmitted to the controller main unit 8 via Bluetooth or Wi-Fi through a wireless communication module for storage. Simultaneously, the remaining power of the battery 10 is ensured to guarantee continuous power supply during training. The patient assumes a sitting or semi-recumbent position, maintaining a clear airway. Holding the trainer main unit, the patient adjusts the rotation angle of the fixing frame 5 using the mounting clip 4 according to their usage habits, ensuring the multiple indicator lights 6 are in the optimal observation position within their field of vision. Then, the sterilized disposable inhalation tube 18 is inserted into the limiting slots 16 on both sides of one end of the breathing tubing 1 through the positioning block 17. After the front end of the positioning block 17 slides into the limiting slot 16, it is rotated a certain angle to engage with the positioning groove on the inner wall of the limiting slot 16, completing the quick locking connection between the inhalation tube 18 and the breathing tubing 1. Ensure that the inspiratory tube 18 does not accidentally come loose during training; the patient tightly wraps their lips around the mouthpiece end of the inspiratory tube 18 and performs a steady and deep inhalation. External air first enters through the insertion hole 11 on the connecting frame 12, and then passes through the coarse filter 14 and the fine filter 15 in the airflow path to complete two-stage filtration and purification, removing large dust particles and fine particulate matter before entering the breathing tube 1. Subsequently, the airflow is diverted into the auxiliary tube 2 and impacts the diaphragm 3, causing the diaphragm 3 to vibrate regularly. The vibration frequency and amplitude are mapped in real time to the patient's actual inspiratory flow rate and respiratory rhythm. The vibration signal is collected by the receiver 7 on the inner wall of the fixed frame 5 and converted into an electrical signal, which is then transmitted to the controller body 8 in real time. The controller body 8 calculates the current actual inspiratory flow and actual respiratory rate according to the built-in algorithm and dynamically compares them with the preset threshold. When the patient's inspiratory force is insufficient or the respiratory rate is too fast or too slow, the controller body 8 controls the LED light groups of different colors to light up according to the degree of deviation. For example, the red light group indicates insufficient flow, the yellow light group indicates that the flow rate is close to the threshold, and the green light group indicates that the standard is met, thus forming a graded excitation indication signal. The patient adjusts his inspiratory force and rhythm in real time according to the lit color, gradually approaching the preset training goal. When the actual respiratory rate is within the preset frequency threshold range and the actual inspiratory flow reaches or exceeds the inspiratory flow threshold, the controller body 8 determines that this breath is an effective deep breath, and then drives all the indicator lights 6 to light up to provide positive reinforcement feedback. At the same time, the timing module inside the controller body 8 starts to record the duration of a single effective breath. When the duration reaches the preset effective duration, the indicator lights 6 flash at a preset frequency to indicate that the patient has fully met the target for this breathing training and can proceed to the next breath.Throughout the training process, the controller body 8 continuously records the vibration signal of each breath, actual respiratory rate data, actual inspiratory flow data, and the illumination record of indicator light 6. This data is then uploaded in real-time to an external smart terminal via a wireless communication module, forming a complete training log. Medical staff can dynamically assess the patient's rehabilitation progress based on the uploaded data and issue adjusted training parameters as needed, ensuring the training plan always aligns with the patient's current lung function status. After training, the patient rotates the positioning block 17 in the opposite direction to disengage its front end from the positioning slot, and removes the inspiratory tube 18 from the limiting slot 16 for disposal or disinfection. Simultaneously, holding the lever 13, pull the connecting frame 12 upwards from the insertion hole 11, clean or replace the coarse filter 14 and fine filter 15, and then reinsert them into the insertion hole 11 to ensure the filtration system maintains good cleanliness for the next use; when the remaining power of the battery 10 is lower than the preset power threshold, the power management module on the circuit board 9 automatically controls the indicator light 6 to light up in low power warning mode to remind the user to charge in time. During the charging process, the power management module monitors the charging current and charging voltage, and automatically cuts off the charging circuit after it is fully charged to ensure battery safety and lifespan.

[0044] Working principle: After the patient covers and seals the mouthpiece of the inhalation tube 18 with their lips, they take a steady and deep breath. External air first enters the dual filtration channel formed by the coarse filter 14 and the fine filter 15 through the insertion hole 11 on the connecting frame 12. The coarse filter 14 initially intercepts large particles of dust and foreign matter in the airflow. The fine filter 15 performs a secondary fine filtration of the airflow after coarse filtration to remove fine particles and some bacteria. The purified air then enters the breathing tube 1. Part of the airflow continues to flow forward along the main channel of the breathing tube 1, while the other part is diverted into the auxiliary tube 2 fixedly connected to the bottom surface of the breathing tube 1. Because a diaphragm 3 is fixedly connected to the inner wall of the auxiliary tube 2, this diverted airflow... As the airflow passes through the auxiliary pipe 2, it directly impacts the surface of the diaphragm 3. Under the impact of the airflow, the diaphragm 3 generates regular forced vibrations that are positively correlated with the real-time inspiratory flow rate and respiratory rhythm. The frequency and amplitude of this vibration change dynamically and synchronously with the patient's actual inspiratory flow rate and respiratory rhythm. The receiver 7, fixedly connected to the inner wall of the fixed frame 5, senses and collects the real-time vibration state of the diaphragm 3 non-contactly or through contact. It converts the mechanical vibration signal of the diaphragm 3 into a corresponding electrical signal and transmits it to the controller body 8, which is electrically connected to the top of the receiver 7. The controller body 8 performs real-time calculations based on the received electrical signal using a built-in algorithm to calculate the patient's current actual inspiratory flow rate and actual respiratory rate. The controller body 8 compares the calculated actual inspiratory flow rate with an internally preset inspiratory flow rate threshold and the actual respiratory rate with an internally preset respiratory rate threshold. When the actual respiratory rate is within the respiratory rate threshold range and the actual inspiratory flow rate reaches the inspiratory flow rate threshold, the controller body 8 determines that the current breathing state is an effective deep breath. It then outputs a corresponding drive control signal through the circuit board 9 electrically connected to its top. Since the circuit board 9 is electrically connected to multiple indicator lights 6 fixedly connected to the surface of the fixed frame 5, the circuit board 9 transmits the drive control signal to the multiple indicator lights 6 to control their illumination, providing immediate positive visual stimulus feedback to the patient. Simultaneously, the timing module inside the controller body 8 starts synchronously, recording the current single breath. The duration of effective breathing is timed. When the preset effective duration is reached, the controller body 8 controls the indicator lights 6 to flash at a preset frequency via the circuit board 9 to indicate to the patient that the deep breathing training has been fully achieved. Throughout the training process, the battery 10 electrically connected to the top of the circuit board 9 serves as the power source, providing continuous and stable power to the receiver 7, controller body 8, circuit board 9, and multiple sets of indicator lights 6, ensuring the normal operation of each electronic component in a portable scenario without an external power supply. The wireless communication module inside the controller body 8 synchronously records the vibration signal of the diaphragm 3 collected by the receiver 7, the actual respiratory rate data and actual inspiratory flow data calculated by the controller body 8, and the data recorded by the indicator lights 6.The data is transmitted in real time to an external smart terminal via Bluetooth or Wi-Fi for remote monitoring, storage, and analysis. Medical staff or users can receive adjustment commands from the external smart terminal and, via the wireless communication module, write updated training parameters into the controller body 8 to dynamically adjust the respiratory rate and inspiratory flow thresholds, thus adapting to the training needs of different rehabilitation stages. When the remaining power of the battery 10 is lower than the preset power threshold of the power management module on the circuit board 9, the power management module automatically controls the indicator light 6 to switch to low power warning mode to remind the user to replenish power in time. The circuit board 9 also has a charging interface electrically connected to the charging input terminal of the battery 10. The power management module monitors the charging current and charging voltage in real time during charging and automatically cuts off the charging circuit after the battery 10 is fully charged to ensure electrical safety. Furthermore, through the fixed connection between the mounting clip 4 and the top surface of the breathing tube 1, and the rotatable connection between the inner wall of the mounting clip 4 and the fixing frame 5, the user can flexibly rotate and adjust the orientation of the fixing frame 5 according to their own usage habits or observation angle requirements, allowing the multiple indicator lights 6 to... The illuminated state is always presented to the user at the optimal visual angle. Simultaneously, the inner walls of the limiting slots 16 on both sides of one end of the breathing tube 1 have positioning grooves. The front end of the positioning block 17 is inserted into the limiting slot 16 and rotated to lock into the positioning groove, achieving a quick locking connection between the inhalation tube 18 and the breathing tube 1 and preventing loosening during training. After training, rotating the positioning block 17 in the opposite direction to disengage its front end from the positioning groove allows the inhalation tube 18 to be pulled out and disassembled. The pull rod 13 fixedly connected to the top of the connecting frame 12 allows the user to apply force by hand, connecting the connecting frame 12 along with the coarse filter 1... 4. The fine filter 15 is pulled out from the insertion hole 11 at the top of the surface of the breathing tube 1 for cleaning or replacement. After cleaning or replacement, the connecting frame 12 is reinserted into the insertion hole 11 to restore the filtering function. Ultimately, the entire trainer, through the coordinated operation of the above structures, forms a complete deep breathing stimulation training closed loop, enabling real-time monitoring, intelligent identification, graded stimulation, remote data transmission, and portable power supply and management of the patient's respiratory rehabilitation training process. This effectively guides the patient to complete deep breathing training with standardized breathing patterns and gradually improve respiratory function.

[0045] The foregoing has only described certain exemplary embodiments of the present invention by way of illustration. Undoubtedly, those skilled in the art can modify the described embodiments in various ways without departing from the spirit and scope of the present invention. Therefore, the foregoing drawings and descriptions are illustrative in nature and should not be construed as limiting the scope of protection of the claims of the present invention.

Claims

1. A portable deep breathing stimulation trainer for respiratory rehabilitation, comprising a breathing tubing (1), characterized in that, An auxiliary tube (2) is fixedly connected to the bottom surface of the breathing tube (1), and a diaphragm (3) is fixedly connected to the inner wall of the auxiliary tube (2). The top surface of the breathing tube (1) is fixedly connected to a mounting clip (4), the inner wall of the mounting clip (4) is rotatably connected to a fixing frame (5), the surface of the fixing frame (5) is fixedly connected to multiple sets of indicator lights (6), the inner wall of the fixing frame (5) is fixedly connected to a receiver (7), the top of the receiver (7) is electrically connected to a controller body (8), the top of the controller body (8) is electrically connected to a circuit board (9), and the circuit board (9) is electrically connected to the indicator lights (6), the top of the circuit board (9) is electrically connected to a battery (10).

2. The portable deep breathing stimulation trainer for respiratory rehabilitation according to claim 1, characterized in that, The top surface of the breathing tube (1) is provided with a plug hole (11), and a connecting frame (12) is plugged into the top of the plug hole (11). A pull rod (13) is fixedly connected to the top of the connecting frame (12).

3. A portable deep breathing stimulation trainer for respiratory rehabilitation according to claim 2, characterized in that, A coarse filter screen (14) is fixedly connected to one side of the inner wall of the connecting frame (12), and a fine filter screen (15) is fixedly connected to the other side of the inner wall of the connecting frame (12).

4. A portable deep breathing stimulation trainer for respiratory rehabilitation according to claim 1, characterized in that, The breathing tube (1) has a limit slot (16) on both sides at one end, and the inner wall of the limit slot (16) has a positioning groove.

5. A portable deep breathing stimulation trainer for respiratory rehabilitation according to claim 4, characterized in that, The inner wall of the limiting slot (16) is fitted with a positioning block (17), and the front end of the positioning block (17) is rotated and inserted into the positioning slot.

6. A portable deep breathing stimulation trainer for respiratory rehabilitation according to claim 5, characterized in that, An air suction pipe (18) is fixedly connected to one side of the positioning block (17).

7. A portable deep breathing stimulation trainer for respiratory rehabilitation according to claim 1, characterized in that, The controller body (8) is preset with a respiratory rate threshold and an inspiratory flow rate threshold. The controller body (8) is used to calculate the actual respiratory rate and the actual inspiratory flow rate based on the vibration signal of the diaphragm (3) received by the receiver (7), and compare the actual respiratory rate with the respiratory rate threshold and the actual inspiratory flow rate with the inspiratory flow rate threshold. When the actual respiratory rate is within the range of the respiratory rate threshold and the actual inspiratory flow rate reaches the inspiratory flow rate threshold, the controller body (8) controls the circuit board (9) to drive the indicator light (6) to light up to indicate the correct breathing state.

8. A portable deep breathing stimulation trainer for respiratory rehabilitation according to claim 7, characterized in that, The indicator light (6) includes multiple groups of LED lights of different colors. The controller body (8) is also used to control the LED lights of different colors to light up according to the deviation between the actual respiratory rate and the respiratory rate threshold, and the deviation between the actual inspiratory flow rate and the inspiratory flow rate threshold, so as to form a graded excitation indication signal. The controller body (8) is also equipped with a timing module, which is used to record the duration of a single effective breath, and when the duration reaches the preset effective duration, the indicator light (6) is controlled to flash at a preset frequency.

9. A portable deep breathing stimulation trainer for respiratory rehabilitation according to claim 1, characterized in that, The controller body (8) is also equipped with a wireless communication module. The wireless communication module is used to transmit the diaphragm (3) vibration signal, actual respiratory rate data, actual inspiratory flow data and indicator light (6) lighting record data received by the receiver (7) to an external smart terminal via Bluetooth or Wi-Fi protocol. The controller body (8) is also used to adjust the respiratory rate threshold and inspiratory flow threshold according to the training parameters issued by the external smart terminal.

10. A portable deep breathing stimulation trainer for respiratory rehabilitation according to claim 1, characterized in that, The output terminal of the battery (10) is electrically connected to the power input terminal of the circuit board (9). The circuit board (9) is provided with a power management module. The power management module is used to detect the remaining power of the battery (10) and control the indicator light (6) to light up in a low power warning mode when the remaining power is lower than the preset power threshold.

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