Rehabilitation breathing exercise device for respiratory medicine department

Abstract

The invention relates to the technical field of rehabilitation respiratory exercise, and discloses a respiratory medicine rehabilitation respiratory exercise device which comprises a respiratory muscle group monitoring module, a training auxiliary module and a dispatching center module. The respiratory muscle group monitoring module comprises a surface myoelectricity detection assembly A, a surface myoelectricity detection assembly B and a surface myoelectricity detection assembly C and is used for monitoring the motion state of specific respiratory muscles, and the surface myoelectricity detection assembly A. The respiratory muscle group monitoring module, the training auxiliary module and the dispatching center module are arranged; surface myoelectricity sensors are arranged in a targeted mode, interference is removed in combination with a self-adaptive filtering algorithm, it is ensured that the muscle force monitoring precision reaches + / -0.1 kPa, data support is provided for personalized training, and countermeasure pressure is dynamically applied at the pressure precision of + / -0.1 kPa through an air bag type pressure assembly on the basis of a muscle force value calculated by a dispatching center, so that the muscle force monitoring precision is improved. The pressure exceeding value can be adjusted within the current muscle force range of 0-40%, and the respiratory muscle training effect is enhanced.

Description

Technical Field

[0001] The present invention relates to the technical field of rehabilitation breathing exercise, in particular to a respiratory medicine rehabilitation breathing exercise device. Background Art

[0002] In the field of elderly care and pulmonary rehabilitation in respiratory medicine, respiratory function training is crucial to improving the patient's respiratory muscle strength and enhancing lung ventilation function. The respiratory training devices currently on the market have many shortcomings: For example, the device with patent number CN212214512U only achieves training through simple pumping, has a single function, cannot accurately monitor the movement status of the respiratory muscles, and is difficult to provide personalized training plans; For example, the system with publication number CN109939419A has a respiratory detection function, but the equipment is complex, costly, and has an unfriendly interface, making it unsuitable for home care scenarios for elderly patients. For example, the trainer with publication number CN114028779A integrates multiple functions, but its structure is bulky, the wearing comfort is poor, and the pressure adjustment lacks real-time dynamic feedback, making it unable to adapt to the characteristics of declining physical functions of elderly patients.

[0003] In addition, the existing devices generally have the following problems: 1. The monitoring accuracy of specific respiratory muscles such as the diaphragm, intercostal muscles, and rectus abdominis is insufficient, and it cannot reflect the dynamic changes of muscles in real time; 2. The pressure assistance module lacks specificity and is unable to provide precise counterpressure based on the strength differences of different muscle groups. 3. The design of the wearable device is not ergonomic, and elderly patients may experience a sense of oppression or difficulty in operation when using it.

[0004] In order to solve the above problems, this application proposes a respiratory rehabilitation breathing exercise device for respiratory medicine. Summary of the Invention

[0005] The object of the present invention is to provide a respiratory rehabilitation exercise device for respiratory medicine to solve the problems in the prior art raised in the above background technology.

[0006] To achieve the above-mentioned object, the present invention provides the following technical solutions: a respiratory rehabilitation exercise device for respiratory medicine, comprising a respiratory muscle group monitoring module, a training auxiliary module and a dispatching center module; The respiratory muscle group monitoring module includes a surface electromyography detection component A, a surface electromyography detection component B, and a surface electromyography detection component C, which are used to monitor the movement state of specific respiratory muscles. The surface electromyography detection component A, the surface electromyography detection component B, and the surface electromyography detection component C correspond to the respiratory muscle group positions of the diaphragm, intercostal muscles, and rectus abdominis, respectively, and can collect the weak electromyography signals generated by these respiratory muscles during the breathing process in real time, and convert them into standard differential signals. The collected analog signals are then converted into digital signals and transmitted to the dispatch center module at a frequency of 200 times per second through a shielded cable or a low-power wireless transmission module; The training assistance module includes a wearable vest, an air pump, an input tube, a transfer head, a pressure component A, a pressure component B, and a pressure component C. The training assistance module is used to provide exercise assistance for specific respiratory muscles. The pressure components A, B, and C are installed on the wearable vest corresponding to the diaphragm, intercostal muscles, and rectus abdominis, respectively. An air pump is installed on one side of the wearable vest, and the output end of the air pump is connected to the input tube, and the other end of the input tube is connected to the transfer head. One side of the transfer head is connected to the pressure components A, B, and C. The air pump and the pressure regulating valve constitute an air pressure control system, which can apply different and dynamically adjustable pressures to the areas where the corresponding muscle groups are located based on the precise control of the scheduling center module. During the respiratory process, the scheduling center module applies different pressures to counteract muscle relaxation to the diaphragm, intercostal muscles, and rectus abdominis in a relaxed state with a pressure accuracy of ±0.1 kPa based on the real-time muscle strength monitoring values of the diaphragm, intercostal muscles, and rectus abdominis provided by the respiratory muscle group monitoring module. The dispatch center module includes a control panel, a signal processing unit, a control unit and a storage unit; the dispatch center module adjusts the muscle force pressure provided by the training auxiliary module for resisting the contraction or relaxation of the specific respiratory muscles based on the specific respiratory muscle movement state provided by the respiratory muscle group monitoring module. When the respiratory muscle group monitoring module detects that the specific respiratory muscle group is in dynamic change, the dispatch center module quickly generates a control instruction within 10 milliseconds through the dynamic change value of the specific respiratory muscle group provided by the respiratory muscle group monitoring module, and accurately controls the training auxiliary module to select the pressure applied to the abdominal area of the trainee to resist the contraction or relaxation of the specific respiratory muscles. The signal processing unit adopts a professional analog-digital mixed signal processing chip. The signal processing unit can receive the electromyographic signal transmitted by the respiratory muscle group monitoring module at a sampling rate of 200-1000 times per second, and uses the built-in anti-aliasing filter and Butterworth low-pass filter algorithm. , denoise and smooth the signal to remove the interference of high-frequency noise and baseline drift, use the signal amplification circuit to amplify the weak electromyographic signal to an amplitude range suitable for subsequent processing, and then use the feature extraction algorithm to extract the characteristic parameters reflecting the respiratory muscle movement state from the processed signal. The control unit quickly calculates the pressure to be applied to each pressure plate area according to the results processed by the signal processing unit and the preset control algorithm that has been clinically verified. The control algorithm comprehensively considers the individual differences of the patient, the rehabilitation stage, and the respiratory muscle movement state of multiple factors, and generates precise control instructions through mathematical models and logical judgments. The control unit sends control instructions to the training auxiliary module with a response speed of milliseconds to ensure the timeliness and accuracy of pressure adjustment. The storage unit can store a large amount of respiratory muscle movement state data, training plans and control algorithm information. The storage unit also supports data interaction with external devices, which facilitates medical staff to analyze and manage data.

[0007] Furthermore, the surface electromyography detection component A includes a surface electromyography sensor A, an adhesive sheet A and a connecting wire A, one end of the control panel is fixedly connected to the connecting wire A, the other end of the connecting wire A is fixedly connected to the surface electromyography sensor A, and the back of the surface electromyography sensor A is provided with an adhesive sheet A; There are two groups of surface electromyography detection components B, each group of surface electromyography detection components B includes three surface electromyography sensors B, an adhesive sheet B and a connecting wire B, one end of the control panel is fixedly connected to the connecting wire B, the other end of the connecting wire B is fixedly connected to the surface electromyography sensor B, and the back of the surface electromyography sensor B is provided with an adhesive sheet B; There are two groups of surface electromyography detection components C, each group of surface electromyography detection components C includes a surface electromyography sensor C, an adhesive sheet C and a connecting line C, one end of the control panel is fixedly connected to the connecting line C, the other end of the connecting line C is fixedly connected to the surface electromyography sensor C, and the back of the surface electromyography sensor C is provided with an adhesive sheet C; During the signal transmission process, the surface electromyography sensors A, B and C use an adaptive filtering algorithm to preprocess the original signals, effectively removing power frequency interference and motion artifact noise, and ensuring that the signals transmitted to the dispatching center module truly reflect the respiratory muscle movement state.

[0008] Furthermore, the surface electromyography sensor A is arranged within 3 cm below the xiphoid process of the human body; The two groups of surface electromyography detection components B are arranged symmetrically on both sides. The surface electromyography sensors B are arranged at positions corresponding to the intercostal muscles in the rib gap. The intervals between the three surface electromyography sensors B in each group are 1.5 cm to 2.5 cm. The two groups of surface electromyography detection components C are arranged symmetrically on the left and right, and the surface electromyography sensors C are arranged at the midline position of the rectus abdominis muscle.

[0009] Furthermore, the wearable vest includes a front piece, a back piece, a Velcro and a Velcro female piece. The top of the front piece is fixedly connected to the back piece, the left and right sides of the bottom end of the front piece are fixedly connected to the Velcro, and the left and right sides of the bottom end of the back piece are fixedly connected to the Velcro female piece.

[0010] Furthermore, the pressure assembly A includes an elastic connecting sleeve A, an airbag A, a memory foam A, a dispersion tube A, a connecting tube A and a pressure control valve A. The front part is fixedly connected to the elastic connecting sleeve A at the position corresponding to the diaphragm. The rear end face of the elastic connecting sleeve A is fixedly connected to the airbag A. The rear end face of the airbag A is fixedly connected to the memory foam A. One end of the airbag A is connected to the dispersion tube A. The other end of the dispersion tube A is connected to the connecting tube A. The other end of the connecting tube A is fixedly connected to the pressure control valve A. The other end of the pressure control valve A is fixedly connected to the transfer head. The pressure assembly B includes an elastic connecting sleeve B, an airbag B, a memory foam B, a dispersion tube B, a connecting tube B and a pressure control valve B. The front part is fixedly connected to the elastic connecting sleeve B at the position corresponding to the intercostal muscles. The rear end face of the elastic connecting sleeve B is fixedly connected to the airbag B. The rear end face of the airbag B is fixedly connected to the memory foam B. One end of the airbag B is connected to the dispersion tube B. The other end of the dispersion tube B is connected to the connecting tube B. The other end of the connecting tube B is fixedly connected to the pressure control valve B. The other end of the pressure control valve B is fixedly connected to the transfer head. The pressure component C includes an elastic connecting sleeve C, an airbag C, a memory foam C, a dispersion tube C, a connecting tube C and a pressure control valve C. The front part is fixedly connected to the elastic connecting sleeve C at the position corresponding to the rectus abdominis muscle. The rear end face of the elastic connecting sleeve C is fixedly connected to the airbag C. The rear end face of the airbag C is fixedly connected to the memory foam C. One end of the airbag C is connected to the dispersion tube C, and the other end of the dispersion tube C is connected to the connecting tube C. The other end of the connecting tube C is fixedly connected to the pressure control valve C, and the other end of the pressure control valve C is fixedly connected to the transfer head.

[0011] Furthermore, the airbag A and the memory foam A are both arranged in a honeycomb shape, the airbag B and the memory foam B are both arranged in a strip shape, and the airbag C and the memory foam C are both arranged in a rectangular shape.

[0012] Furthermore, an auxiliary pressure assembly is installed on the back part, and the auxiliary pressure assembly includes three airbags D, an auxiliary tube and an auxiliary pump. The front side of the back part is fixedly connected to the airbag D, one side of the airbag D is connected to the auxiliary tube, and the other end of the auxiliary tube is fixedly connected to the output end of the auxiliary pump.

[0013] Furthermore, the pressure components A, B and C are connected to the dispatching center module through a high-speed data communication interface to ensure the rapid transmission of control instructions. The dispatching center module obtains the characteristic parameters of the myoelectric signal of the diaphragm, intercostal muscles and rectus abdominis through a built-in electromyographic signal analysis algorithm, and calculates the current muscle strength of the diaphragm, intercostal muscles and rectus abdominis in real time based on a mathematical formula verified by a large amount of clinical data. The dispatching center module sends control instructions to pressure components A and / or B and / or C at a frequency of not less than 200 times per second based on the calculation results, controlling pressure component A to apply a pressure greater than the current muscle strength of the diaphragm, controlling pressure component B to apply a pressure greater than the current muscle strength of the intercostal muscles, and controlling pressure component C to apply a pressure greater than the current muscle strength of the rectus abdominis, so as to control the exercise of the auxiliary diaphragm and / or intercostal muscles and / or rectus abdominis.

[0014] Furthermore, the pressure applied by the pressure component A exceeds the current muscle strength of the diaphragm by a value of F1, the pressure applied by the pressure component B exceeds the current muscle strength of the intercostal muscles by a value of F2, and the pressure applied by the pressure component C exceeds the current muscle strength of the rectus abdominis by a value of F3. The sizes of F1, F2 and F3 are manually set on the control panel of the dispatch center module according to the patient's recovery stage and physical condition, and the range corresponds to 0%-40% of the current muscle strength.

[0015] Compared with the prior art, the present invention has the following beneficial effects: 1. The present invention adopts the respiratory muscle monitoring module, training auxiliary module and dispatching center module, and adopts the targeted arrangement of surface electromyographic sensors (arranged in the corresponding positions of the diaphragm, intercostal muscles and rectus abdominis muscles respectively), collects electromyographic signals in real time at a sampling rate of 200 times per second, and combines with the adaptive filtering algorithm to remove interference, ensuring the muscle force monitoring accuracy of ±0.1kPa, providing data support for personalized training. The training auxiliary module uses the airbag pressure component (honeycomb, strip and rectangular structures correspond to the diaphragm, intercostal muscles and rectus abdominis muscles respectively) to dynamically apply the counterpressure with a pressure accuracy of ±0.1kPa based on the muscle force value calculated by the dispatching center. For example, the diaphragm pressure excess value F1 can be adjusted within the current muscle force range of 0-40%, effectively enhancing the respiratory muscle training effect.

[0016] 2. The wearable vest of the present invention adopts a Velcro adjustable structure, combined with a memory foam cushion layer and an elastic connecting sleeve, which fits the body curve of elderly patients and reduces the sense of oppression.

[0017] 3. The operating convenience of the operation panel in the present invention is significantly improved. The dispatch center processes electromyographic signals in real time through a high-speed communication interface, calculates muscle strength based on clinically verified mathematical formulas, and adjusts pressure at a frequency of 200 times per second; the wireless communication module supports remote transmission of training data to the medical terminal, realizing dynamic tracking of the rehabilitation process. BRIEF DESCRIPTION OF THE DRAWINGS

[0018] Figure 1 This is a schematic diagram of the overall structure of a respiratory rehabilitation exercise device for respiratory medicine of the present invention; Figure 2 This is a schematic diagram of the installation structure of a respiratory muscle group monitoring module of a respiratory rehabilitation exercise device for respiratory medicine of the present invention; Figure 3 This is a rear view of the installation structure of a training auxiliary module of a respiratory rehabilitation breathing exercise device of the present invention; Figure 4 This is a schematic diagram of the unfolded structure of a wearable vest for a respiratory rehabilitation breathing exercise device of the present invention; Figure 5 This is a structural schematic diagram of a pressure component A of a respiratory rehabilitation breathing exercise device of the present invention; Figure 6 This is a structural schematic diagram of a pressure component B of a respiratory rehabilitation breathing exercise device of the present invention; Figure 7 This is a schematic structural diagram of a pressure component C of a respiratory rehabilitation breathing exercise device of the present invention; Figure 8 This is a schematic diagram of the installation structure of an auxiliary pressure component of a respiratory rehabilitation breathing exercise device of the present invention; Figure 9This is a diagram of the overall structure of a respiratory rehabilitation exercise device for respiratory medicine according to the present invention; In the picture: 1. Respiratory muscle monitoring module; 11. Surface electromyography (EMG) detection component A; 111. Surface electromyography (EMG) sensor A; 112. Adhesive patch A; 113. Connecting cable A; 12. Surface electromyography (EMG) detection component B; 121. Surface electromyography (EMG) sensor B; 122. Adhesive patch B; 123. Connecting cable B; 13. Surface electromyography (EMG) detection component C; 131. Surface electromyography (EMG) sensor C; 132. Adhesive patch C; 133. Connecting cable C; 2. Training auxiliary module; 21. Wearing vest; 211. Front piece; 212. Back piece; 213. Velcro; 214. Velcro; 22. Air pump; 23. Input tube; 24. Transfer head; 25. Pressure component A; 251. Elastic connecting sleeve A; 252. Air bag A; 253. Memory foam A; 254. Dispersion tube A; 255. Connecting tube A; 256. Pressure control valve A; 26. Pressure component B; 261. Elastic connecting sleeve B; 262. Air bag B; 263. Memory foam B; 264. Dispersion tube B; 265. Connecting tube B; 266. Pressure control valve B; 27. Pressure component C; 271. Elastic connecting sleeve C; 272. Air bag C; 273. Memory foam C; 274. Dispersion tube C; 275. Connecting tube C; 276. Pressure control valve C.

[0019] 3. Dispatching center module; 31. Control panel; 32. Signal processing unit; 33. Control unit; 34. Storage unit.

[0020] 4. Auxiliary pressure assembly; 41. Airbag D; 42. Auxiliary tube; 43. Auxiliary pump. DETAILED DESCRIPTION

[0021] The technical solutions in the embodiments of the present invention will be clearly and completely described below in conjunction with the drawings in the embodiments of the present invention. Obviously, the described embodiments are only part of the embodiments of the present invention, rather than all the embodiments.

[0022] The standard parts used in this application can all be purchased from the market, and special-shaped parts can be customized according to the instructions and drawings. The specific connection methods of each part adopt conventional means such as mature bolts, rivets, welding, and bonding in the existing technology, and the components used for circuit connection are all conventional models in the existing technology.

[0023] At the same time, in order to clearly express the connection relationship and working principle between the various components and highlight the key points, the drawings in the specification are organized and drawn in the form of simple diagrams. One simple diagram can correspond to a variety of materials and actual external structural shapes. Example

[0024] See also Figures 1-9 , the present invention provides a technical solution: a respiratory rehabilitation exercise device for respiratory medicine, comprising a respiratory muscle group monitoring module 1, a training auxiliary module 2 and a dispatching center module 3; The respiratory muscle group monitoring module 1 includes a surface electromyography detection component A11, a surface electromyography detection component B12 and a surface electromyography detection component C13, which are used to monitor the movement state of specific respiratory muscles. The surface electromyography detection component A11, the surface electromyography detection component B12 and the surface electromyography detection component C13 correspond to the respiratory muscle group positions of the diaphragm, intercostal muscles and rectus abdominis respectively, and can collect the weak electromyography signals generated by these respiratory muscles during the breathing process in real time, and convert them into standard differential signals. The collected analog signals are then converted into digital signals and transmitted to the dispatch center module 3 at a frequency of 200 times per second through a shielded cable or a low-power wireless transmission module; The training auxiliary module 2 includes a wearing vest 21, an air pump 22, an input tube 23, a transfer head 24, a pressure component A25, a pressure component B26 and a pressure component C27. The training auxiliary module 2 is used to provide exercise assistance for specific respiratory muscles. The pressure components A25, B26 and C27 are respectively installed on the wearing vest 21 corresponding to the diaphragm, intercostal muscles and rectus abdominis muscles. An air pump 22 is installed on one side of the wearing vest 21. The output end of the air pump 22 is connected to the input tube 23. The other end of the input tube 23 is connected to the transfer head 24. One side of the transfer head 24 The air pump 22 and the pressure regulating valve are connected to the pressure components A25, B26, and C27, and form an air pressure control system. Based on the precise control of the dispatch center module 3, the dispatch center module 3 can apply different and dynamically adjustable pressures to the areas where the corresponding muscle groups are located. During the respiratory process, the dispatch center module 3 applies different pressures to counteract muscle relaxation to the diaphragm, intercostal muscles, and rectus abdominis muscles in the relaxed state with a pressure accuracy of ±0.1 kPa according to the real-time muscle strength monitoring values of the diaphragm, intercostal muscles, and rectus abdominis provided by the respiratory muscle group monitoring module 1. The dispatch center module 3 includes a control panel 31, a signal processing unit 32, a control unit 33 and a storage unit 34. The dispatch center module 3 adjusts the muscle force pressure generated in the movement state of the specific respiratory muscles provided by the training auxiliary module 2 to counteract the contraction or relaxation of the specific respiratory muscles based on the specific respiratory muscle movement state provided by the respiratory muscle group monitoring module 1. When the respiratory muscle group monitoring module 1 detects that the specific respiratory muscle group is in dynamic change, the dispatch center module 3 quickly generates a control instruction within 10 milliseconds through the dynamic change value of the specific respiratory muscle group provided by the respiratory muscle group monitoring module 1, and accurately controls the training auxiliary module 2 to select the pressure applied to the abdominal area of the trainee to counteract the contraction or relaxation of the specific respiratory muscles. The signal processing unit 32 adopts a professional analog-digital mixed signal processing chip. The signal processing unit can receive the electromyographic signal transmitted by the respiratory muscle group monitoring module 1 at a sampling rate of 200-1000 times per second, and pass it through the built-in anti-aliasing filter and Butterworth low-pass filter. The filtering algorithm denoises and smoothes the signal to remove the interference of high-frequency noise and baseline drift, and uses a signal amplification circuit to amplify the weak electromyographic signal to an amplitude range suitable for subsequent processing. Then, through the feature extraction algorithm, characteristic parameters reflecting the respiratory muscle movement state are extracted from the processed signal. The control unit 33 quickly calculates the pressure required to be applied to each pressure plate area according to the results processed by the signal processing unit 32 and a preset control algorithm that has been clinically verified. The control algorithm comprehensively considers multiple factors such as individual differences of patients, rehabilitation stage, and respiratory muscle movement state, and generates precise control instructions through mathematical models and logical judgments. The control unit 33 sends control instructions to the training auxiliary module 2 at a response speed of milliseconds to ensure the timeliness and accuracy of pressure adjustment. The storage unit 34 can store a large amount of respiratory muscle movement state data, training plans, and control algorithm information. The storage unit 34 also supports data interaction with external devices, making it convenient for medical staff to analyze and manage data.

[0025] It should be noted that the surface electromyographic signal (sEMG) contains multiple information such as amplitude and frequency. The key characteristic parameters are extracted through the following algorithm: Root mean square value (RMS): reflects the strength of the electromyographic signal. The formula is: Among them, x i is the electromyographic signal value of the i-th sampling point, N is the number of sampling points, and this parameter can reflect the strength of muscle contraction; Mean Absolute Value (MAV): Calculates the average of the absolute values of the signal. The formula is: MAV can also reflect the intensity of muscle activity, and its computational complexity is lower; Power spectral density (PSD): Analyzes the energy distribution of a signal at different frequencies, often calculated using fast Fourier transform (FFT). The dominant frequencies in the PSD (e.g., the energy proportions in the low-frequency band (10-50 Hz) and the high-frequency band (50-150 Hz)) can reflect the degree of muscle fatigue and contraction state. Zero crossing rate (ZC) calculation: Count the number of times the electromyographic signal crosses the zero level per unit time. The formula is: , where T is the time interval, sgn is the sign function, when hour, The surface electromyography detection component A11 includes a surface electromyography sensor A111, an adhesive sheet A112 and a connecting wire A113. One end of the control panel 31 is fixedly connected to the connecting wire A113, and the other end of the connecting wire A113 is fixedly connected to the surface electromyography sensor A. The back of the surface electromyography sensor A is provided with an adhesive sheet A112. There are two groups of surface electromyography detection components B12, each group of surface electromyography detection components B12 includes three surface electromyography sensors B121, an adhesive sheet B122 and a connecting wire B123. One end of the control panel 31 is fixedly connected to the connecting wire B123, and the other end of the connecting wire B123 is fixedly connected to the surface electromyography sensor B. The back of the surface electromyography sensor B is provided with an adhesive sheet B122. There are two groups of surface electromyography detection components C13, each group of surface electromyography detection components C13 includes a surface electromyography sensor C131, an adhesive sheet C132 and a connecting wire C133. One end of the control panel 31 is fixedly connected to the connecting wire C133, and the other end of the connecting wire C133 is fixedly connected to the surface electromyography sensor C. The back of the surface electromyography sensor C is provided with an adhesive sheet C132. During the signal transmission process, the surface electromyography sensor A111, surface electromyography sensor B121 and surface electromyography sensor C131 use an adaptive filtering algorithm to preprocess the original signal, effectively removing the noise of power frequency interference and motion artifacts, and ensuring that the signal transmitted to the dispatch center module 3 truly reflects the respiratory muscle movement state.

[0026] The surface electromyography sensor A111 is set within 3 cm below the xiphoid process of the human body; The two groups of surface electromyography detection components B12 are symmetrically arranged, and the surface electromyography sensors B121 are arranged at positions corresponding to the intercostal muscles in the rib gap, and the intervals between the three surface electromyography sensors B121 in each group are 1.5 cm to 2.5 cm; The two groups of surface electromyography detection components C13 are symmetrically arranged on the left and right, and the surface electromyography sensor C131 is arranged at the midline position of the rectus abdominis muscle.

[0027] The wearing vest 21 includes a front piece 211, a back piece 212, a Velcro 213 and a Velcro mother patch 214. The top of the front piece 211 is fixedly connected to the back piece 212, the left and right sides of the bottom end of the front piece 211 are fixedly connected to the Velcro 213, and the left and right sides of the bottom end of the north piece are fixedly connected to the Velcro mother patch 214. The front piece 211 is ahead and the back piece 212 is backward. It is worn through the head, and then the Velcro mother patch 214 is glued to the Velcro word patch 213 to complete the wearing of the wearing vest 21.

[0028] The pressure assembly A25 includes an elastic connecting sleeve A251, an airbag A252, a memory foam A253, a dispersion tube A254, a connecting tube A255 and a pressure control valve A256. The front part 211 is fixedly connected to the elastic connecting sleeve A251 at the position corresponding to the diaphragm. The rear end face of the elastic connecting sleeve A251 is fixedly connected to the airbag A252. The rear end face of the airbag A252 is fixedly connected to the memory foam A253. One end of the airbag A252 is connected to the dispersion tube A254. The other end of the dispersion tube A254 is connected to the connecting tube A255. The other end of the connecting tube A255 is fixedly connected to the pressure control valve A256. The other end of the pressure control valve A256 is fixedly connected to the transfer head 24. The pressure assembly B26 includes an elastic connecting sleeve B261, an airbag B262, a memory foam B263, a dispersion tube B264, a connecting tube B265 and a pressure control valve B266. The front part 211 is fixedly connected to the elastic connecting sleeve B261 at the position corresponding to the intercostal muscles. The rear end face of the elastic connecting sleeve B261 is fixedly connected to the airbag B262. The rear end face of the airbag B262 is fixedly connected to the memory foam B263. One end of the airbag B262 is connected to the dispersion tube B264. The other end of the dispersion tube B264 is connected to the connecting tube B265. The other end of the connecting tube B265 is fixedly connected to the pressure control valve B266. The other end of the pressure control valve B266 is fixedly connected to the transfer head 24. The pressure component C27 includes an elastic connecting sleeve C271, an airbag C272, a memory foam C273, a dispersion tube C274, a connecting tube C275 and a pressure control valve C276. The front part 211 is fixedly connected to the elastic connecting sleeve C271 at the position corresponding to the rectus abdominis muscle. The rear end face of the elastic connecting sleeve C271 is fixedly connected to the airbag C272. The rear end face of the airbag C272 is fixedly connected to the memory foam C273. One end of the airbag C272 is connected to the dispersion tube C274. The other end of the dispersion tube C274 is connected to the connecting tube C275. The other end of the connecting tube C275 is fixedly connected to the pressure control valve C276. The other end of the pressure control valve C276 is fixedly connected to the transfer head 24.

[0029] The airbag A252 and memory foam A253 are both arranged in a honeycomb shape, the airbag B262 and memory foam B263 are both arranged in a strip shape, and the airbag C272 and memory foam C273 are both arranged in a rectangular shape, which can better fit the corresponding muscles. An auxiliary pressure assembly 4 is also installed on the back part 212. The auxiliary pressure assembly 4 includes three airbags D41, an auxiliary tube 42 and an auxiliary pump 43. The front side of the back part 212 is fixedly connected to the airbag D41, one side of the airbag D41 is connected to the auxiliary tube 42, and the other end of the auxiliary tube 42 is fixedly connected to the output end of the auxiliary pump 43. After the device is worn, the auxiliary pump 43 runs through the auxiliary tube 42 to supply air to the airbag D41, so that the airbag A252 can better apply pressure to the memory foam A253, thereby improving the stability of providing pressure to the diaphragm, so that the airbag B262 can better apply pressure to the memory foam B263, thereby improving the stability of providing pressure to the intercostal muscles, and so that the airbag C272 can better apply pressure to the memory foam C273, thereby improving the stability of providing pressure to the rectus abdominis. The pressure components A25, B26 and C27 are connected to the dispatch center module 3 via a high-speed data communication interface to ensure the rapid transmission of control instructions. The dispatch center module 3 obtains the characteristic parameters of the myoelectric signals of the diaphragm, intercostal muscles and rectus abdominis through a built-in electromyographic signal analysis algorithm, and calculates the current muscle strength of the diaphragm, intercostal muscles and rectus abdominis in real time based on a mathematical formula verified by a large amount of clinical data. The dispatch center module 3 sends control instructions to the pressure components A25 and / or B26 and / or C27 at a frequency of not less than 200 times per second based on the calculation results, controlling the pressure component A25 to apply a pressure greater than the current muscle strength of the diaphragm, controlling the pressure component B26 to apply a pressure greater than the current muscle strength of the intercostal muscles, and controlling the pressure component C27 to apply a pressure greater than the current muscle strength of the rectus abdominis, so as to control the exercise of the auxiliary diaphragm and / or intercostal muscles and / or rectus abdominis.

[0030] It should be noted that based on a large amount of clinical experimental data (recruiting patients of different age groups, health conditions and lung disease types, and synchronously collecting electromyographic signals and actual diaphragm muscle strength measured by respiratory mechanics equipment), a formula was established using multiple linear regression: ,in, is the estimated diaphragm muscle strength, a, b, c are the regression coefficients obtained by least squares fitting, It is the ratio of the power spectrum density of the low-frequency band to that of the high-frequency band, reflecting the degree of muscle fatigue, and d is a constant term.

[0031] It should be noted that in addition to the root mean square (RMS), mean absolute value (MAV), power spectral density (PSD), and zero-crossing rate (ZC), the respiratory rate correlation coefficient (RFC) is introduced, considering that the intercostal muscles participate in the expansion and contraction of the thorax during respiration, and their movement amplitude and speed are related to the respiratory rate. The number of breaths per unit time is obtained by analyzing the respiratory signal and then normalized to obtain the RFC.

[0032] In addition, since the intercostal muscles are subjected to different forces in different respiratory phases (inhalation and exhalation), the respiratory phase coefficient (RSC) is introduced. The RSC is 1 during inhalation and -1 during exhalation. The formula is established using multiple linear regression: in, is the predicted intercostal muscle strength, β0, β 1、 β 2、 β 3、 β 4、 β5 is the regression coefficient, It is the ratio of the power spectral density of the low-frequency band to the high-frequency band of the intercostal muscle electromyography signal, reflecting the degree of muscle fatigue.

[0033] It should be noted that the rectus abdominis muscle mainly assists the diaphragm in abdominal breathing during breathing, and its contraction is closely related to changes in abdominal pressure. In addition to the root mean square value (RMS), mean absolute value (MAV), power spectral density (PSD), and zero-crossing rate (ZC), the abdominal pressure change rate (APCR) is introduced. The abdominal pressure change is monitored in real time through a pressure sensor, and the pressure change value per unit time is calculated and normalized to obtain the APCR.

[0034] At the same time, considering that there may be unbalanced force on the left and right sides of the rectus abdominis, the left-right side force difference coefficient (LSDC) is introduced. It is calculated by comparing the difference in the electromyographic signal intensity of the left and right rectus abdominis muscles. The range is between -1 and 1, and 0 indicates balanced force on both sides. The formula is established using multiple linear regression: in, is the predicted rectus abdominis muscle strength, γ0, γ1, γ2, γ3, γ4, γ5, γ6 are regression coefficients, Focus on the power spectrum density of the high-frequency band of the rectus abdominis electromyographic signal, which reflects the muscle's ability to contract rapidly.

[0035] The pressure applied by the pressure component A25 exceeds the current muscle strength of the diaphragm by a value of F1, the pressure applied by the pressure component B26 exceeds the current muscle strength of the intercostal muscles by a value of F2, and the pressure applied by the pressure component C27 exceeds the current muscle strength of the rectus abdominis by a value of F3. The sizes of F1, F2 and F3 are manually set on the control panel 31 of the dispatch center module 3 according to the patient's recovery stage and physical condition, and the range corresponds to 0%-40% of the current muscle strength.

Claims

1. A respiratory rehabilitation exercise device for respiratory medicine, characterized by: It includes a respiratory muscle group monitoring module (1), a training auxiliary module (2) and a dispatch center module (3); The respiratory muscle group monitoring module (1) includes a surface electromyography detection component A (11), a surface electromyography detection component B (12) and a surface electromyography detection component C (13), which are used to monitor the movement state of specific respiratory muscles. The surface electromyography detection component A (11), the surface electromyography detection component B (12) and the surface electromyography detection component C (13) correspond to the respiratory muscle group positions of the diaphragm, intercostal muscles and rectus abdominis muscles respectively, and can collect the weak electromyography signals generated by these respiratory muscles during the breathing process in real time and convert them into standard differential signals. The collected analog signals are then converted into digital signals and transmitted to the dispatch center module (3) at a frequency of 200 times per second through a shielded cable or a low-power wireless transmission module; The training auxiliary module (2) comprises a wearable vest (21), an air pump (22), an input tube (23), a transfer head (24), a pressure component A (25), a pressure component B (26) and a pressure component C (27). The training auxiliary module (2) is used to provide exercise assistance for specific respiratory muscles. The pressure component A (25), the pressure component B (26) and the pressure component C (27) are respectively installed on the wearable vest (21) corresponding to the diaphragm, the intercostal muscles and the rectus abdominis muscles. The air pump (22) is installed on one side of the wearable vest (21). The output end of the air pump (22) is connected to the input tube (23), and the other end of the input tube (23) is connected to the transfer head (24). ), one side of the intermediate transfer head (24) is connected to the pressure component A (25), the pressure component B (26) and the pressure component C (27), and the air pump (22) and the pressure regulating valve form an air pressure control system, which can apply different sizes of dynamically adjustable pressure to the area where the corresponding muscle group is located based on the precise control of the dispatching center module (3). When entering the breathing process, the dispatching center module (3) applies different sizes of pressure for resisting muscle relaxation to the diaphragm, intercostal muscles and rectus abdominis muscles in the relaxation state with a pressure accuracy of ±0.1kPa based on the real-time muscle strength monitoring values of the diaphragm, intercostal muscles and rectus abdominis muscles provided by the respiratory muscle group monitoring module (1).

2. A respiratory rehabilitation breathing exercise device according to claim 1, characterized in that: The surface electromyography detection component A (11) includes a surface electromyography sensor A (111), an adhesive sheet A (112) and a connecting wire A (113); one end of the control panel (31) is fixedly connected to the connecting wire A (113); the other end of the connecting wire A (113) is fixedly connected to the surface electromyography sensor A (111); and the back of the surface electromyography sensor A (111) is provided with an adhesive sheet A (112); The number of groups of the surface electromyography detection components B (12) is two, and each group of the surface electromyography detection components B (12) includes three surface electromyography sensors B (121), an adhesive sheet B (122), and a connecting wire B (123); one end of the control panel (31) is fixedly connected to the connecting wire B (123), and the other end of the connecting wire B (123) is fixedly connected to the surface electromyography sensor B (121); and the back of the surface electromyography sensor B (121) is provided with an adhesive sheet B (122); The number of groups of the surface electromyography detection components C (13) is two, and each group of the surface electromyography detection components C (13) includes a surface electromyography sensor C (131), an adhesive sheet C (132), and a connecting wire C (133); one end of the control panel (31) is fixedly connected to the connecting wire C (133), and the other end of the connecting wire C (133) is fixedly connected to the surface electromyography sensor C (131); and the back of the surface electromyography sensor C (131) is provided with an adhesive sheet C (132); During the signal transmission process, the surface electromyography sensor A (111), the surface electromyography sensor B (121) and the surface electromyography sensor C (131) use an adaptive filtering algorithm to pre-process the original signal, effectively removing the noise of power frequency interference and motion artifacts, and ensuring that the signal transmitted to the dispatch center module (3) truly reflects the movement state of the respiratory muscles.

3. The respiratory rehabilitation breathing exercise device according to claim 2, characterized in that: The surface electromyography sensor A (111) is arranged within 3 cm below the xiphoid process of the human body; The two groups of surface electromyography detection components B (12) are symmetrically arranged on both sides, and the surface electromyography sensors B (121) are arranged at positions corresponding to the intercostal muscles in the intercostal space, and the intervals between the three surface electromyography sensors B (121) in each group are 1.5 cm to 2.5 cm; The two groups of surface electromyography detection components C (13) are arranged symmetrically on both sides, and the surface electromyography sensor C (131) is arranged at the midline position of the rectus abdominis muscle.

4. The respiratory rehabilitation breathing exercise device according to claim 1, characterized in that: The wearable vest (21) comprises a front piece (211), a back piece (212), a Velcro (213) and a Velcro mother piece (214), wherein the top of the front piece (211) is fixedly connected to the back piece (212), the left and right sides of the bottom end of the front piece (211) are fixedly connected to the Velcro (213), and the left and right sides of the bottom end of the back piece are fixedly connected to the Velcro mother piece (214).

5. The respiratory rehabilitation breathing exercise device according to claim 4, characterized in that: The pressure assembly A (25) includes an elastic connecting sleeve A (251), an airbag A (252), a memory foam A (253), a dispersion tube A (254), a connecting tube A (255) and a pressure control valve A (256); the front part (211) is fixedly connected to the elastic connecting sleeve A (251) at a position corresponding to the diaphragm; the rear end face of the elastic connecting sleeve A (251) is fixedly connected to the airbag A (252); the rear end face of the airbag A (252) is fixedly connected to the memory foam A (253); one end of the airbag A (252) is connected to the dispersion tube A (254); the other end of the dispersion tube A (254) is connected to the connecting tube A (255); the other end of the connecting tube A (255) is fixedly connected to the pressure control valve A (256); the other end of the pressure control valve A (256) is fixedly connected to the intermediate transfer head (24); The pressure assembly B (26) includes an elastic connecting sleeve B (261), an airbag B (262), a memory foam B (263), a dispersion tube B (264), a connecting tube B (265) and a pressure control valve B (266); the front part (211) is fixedly connected to the elastic connecting sleeve B (261) at a position corresponding to the intercostal muscles; the rear end face of the elastic connecting sleeve B (261) is fixedly connected to the airbag B (262); the rear end face of the airbag B (262) is fixedly connected to the memory foam B (263); one end of the airbag B (262) is connected to the dispersion tube B (264); the other end of the dispersion tube B (264) is connected to the connecting tube B (265); the other end of the connecting tube B (265) is fixedly connected to the pressure control valve B (266); the other end of the pressure control valve B (266) is fixedly connected to the intermediate transfer head (24); The pressure assembly C (27) comprises an elastic connecting sleeve C (271), an airbag C (272), a memory foam C (273), a dispersion tube C (274), a connecting tube C (275) and a pressure control valve C (276). The front member (211) is fixedly connected to the elastic connecting sleeve C (271) at a position corresponding to the rectus abdominis muscle. The rear end face of the elastic connecting sleeve C (271) is fixedly connected to the airbag C (272). The rear end face of the airbag C (272) is fixedly connected to the memory foam C (273). One end of the airbag C (272) is connected to the dispersion tube C (274). The other end of the dispersion tube C (274) is connected to the connecting tube C (275). The other end of the connecting tube C (275) is fixedly connected to the pressure control valve C (276). The other end of the pressure control valve C (276) is fixedly connected to the intermediate transfer head (24).

6. The respiratory rehabilitation breathing exercise device according to claim 5, characterized in that: The airbag A (252) and the memory foam A (253) are both arranged in a honeycomb shape, the airbag B (262) and the memory foam B (263) are both arranged in a strip shape, and the airbag C (272) and the memory foam C (273) are both arranged in a rectangular shape.

7. The respiratory rehabilitation breathing exercise device according to claim 6, characterized in that: An auxiliary pressure assembly (4) is also installed on the back member (212), and the auxiliary pressure assembly (4) includes three airbags D (41), an auxiliary tube (42) and an auxiliary pump (43). The front side of the back member (212) is fixedly connected to the airbag D (41), one side of the airbag D (41) is connected to the auxiliary tube (42), and the other end of the auxiliary tube (42) is fixedly connected to the output end of the auxiliary pump (43).

8. The respiratory rehabilitation breathing exercise device according to claim 1, characterized in that: The pressure component A (25), pressure component B (26) and pressure component C (27) are connected to the dispatch center module (3) through a high-speed data communication interface to ensure the rapid transmission of control instructions. The dispatch center module (3) obtains the myoelectric signal characteristic parameters of the diaphragm, intercostal muscles and rectus abdominis through a built-in electromyographic signal analysis algorithm, and calculates the current muscle strength of the diaphragm, intercostal muscles and rectus abdominis in real time based on a mathematical formula verified by a large amount of clinical data. According to the calculation results, the dispatch center module (3) sends control instructions to the pressure component A (25) and / or pressure component B (26) and / or pressure component C (27) at a frequency of not less than 200 times per second, controlling the pressure component A (25) to apply a pressure greater than the current muscle strength of the diaphragm, controlling the pressure component B (26) to apply a pressure greater than the current muscle strength of the intercostal muscles, and controlling the pressure component C (27) to apply a pressure greater than the current muscle strength of the rectus abdominis, so as to control the training of the auxiliary diaphragm and / or intercostal muscles and / or rectus abdominis.

9. The respiratory rehabilitation breathing exercise device according to claim 1, characterized in that: The pressure applied by the pressure component A (25) exceeds the current muscle strength of the diaphragm by a value of F1, the pressure applied by the pressure component B (26) exceeds the current muscle strength of the intercostal muscles by a value of F2, and the pressure applied by the pressure component C (27) exceeds the current muscle strength of the rectus abdominis by a value of F3. The sizes of F1, F2 and F3 are manually set on the control panel (31) of the dispatch center module (3) according to the patient's recovery stage and physical condition, and the range corresponds to 0%-40% of the current muscle strength.

10. The respiratory rehabilitation breathing exercise device according to claim 1, characterized in that: The dispatch center module (3) includes a control panel (31), a signal processing unit (32), a control unit (33) and a storage unit (34); the dispatch center module (3) adjusts the muscle force pressure provided by the training auxiliary module (2) for resisting the specific respiratory muscle contraction or relaxation based on the specific respiratory muscle movement state provided by the respiratory muscle group monitoring module (1); when the respiratory muscle group monitoring module (1) detects that the specific respiratory muscle group is in a dynamic change, the dispatch center module (3) quickly generates a control instruction within 10 milliseconds based on the dynamic change value of the specific respiratory muscle group provided by the respiratory muscle group monitoring module (1), and accurately controls the training auxiliary module (2) to select the pressure applied to the abdominal area of the trainee for resisting the specific respiratory muscle contraction or relaxation. The signal processing unit (32) adopts a professional analog-digital mixed signal processing chip. The signal processing unit can receive the electromyographic signal transmitted by the respiratory muscle group monitoring module (1) at a sampling rate of 200-1000 times per second, and through the built-in anti-aliasing filter, Bart The filtering algorithm of the Voss low-pass filter performs denoising and smoothing processing on the signal, removes the interference of high-frequency noise and baseline drift, uses a signal amplification circuit to amplify the weak electromyographic signal to an amplitude range suitable for subsequent processing, and then extracts characteristic parameters reflecting the respiratory muscle movement state from the processed signal through a feature extraction algorithm. The control unit (33) quickly calculates the pressure required to be applied to each pressure plate area according to the result processed by the signal processing unit (32) and a preset control algorithm that has been clinically verified. The control algorithm comprehensively considers multiple factors such as individual differences of patients, rehabilitation stage, and respiratory muscle movement state, and generates accurate control instructions through mathematical models and logical judgments. The control unit (33) sends control instructions to the training auxiliary module (2) at a response speed of milliseconds to ensure the timeliness and accuracy of pressure adjustment. The storage unit (34) can store a large amount of respiratory muscle movement state data, training programs, and control algorithm information. The storage unit (34) also supports data interaction with external devices, making it convenient for medical staff to analyze and manage data.

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