A physiotherapy instrument pulse control method and control system

Abstract

This invention discloses a control method and control system for pulses in a physiotherapy device. The method includes: acquiring detection data collected by the patch during its operation; wherein the detection data includes: electromyography (EMG) data, skin impedance, skin temperature, and pressure distribution; identifying the patch's fit degree based on the skin impedance and pressure distribution; after the fit degree meets the standard, determining the current operating state category of the physiotherapy device based on the EMG data and skin temperature; obtaining electrode current compensation and heating power compensation for the patch based on the operating state category; and controlling the patch to adjust the current pulse and temperature based on the electrode current compensation and heating power compensation. This invention solves the technical problem in the prior art where physiotherapy devices cannot adaptively adjust different pulse controls for output, and can automatically adjust the current pulse and temperature parameters to suit the user when using the physiotherapy device, improving the user experience and ease of use.

Description

Technical Field

[0001] This invention relates to the field of physiotherapy instrument control technology, and in particular to a method and control system for controlling pulses in a physiotherapy instrument. Background Technology

[0002] Physiotherapy devices are specialized instruments designed for people with physiotherapy and massage needs. They stimulate muscle contraction by controlling the output current of patch electrodes, thereby achieving a soothing massage effect. Currently, physiotherapy devices based on muscle electrical stimulation technology on the market have different modes set for different physiotherapy needs, such as hand and waist therapy. The default operating parameters such as current pulse intensity and temperature are different for the corresponding control modes. They are also equipped with voice recognition and control functions, allowing users to switch modes and adjust parameters through voice input.

[0003] Current physiotherapy devices can only control the output pulses based on specific therapeutic needs (i.e., control modes corresponding to needs in the hands, waist, etc.). For different users, individual differences mean that different people are affected by the pulse stimulation to varying degrees. Therefore, when using the default mode of the physiotherapy device, the pulse current stimulation controlled by the device may not actually meet the user's expectations or may have exceeded the user's body's tolerance range. Furthermore, because users may lack relevant professional knowledge, even if the physiotherapy device can switch modes and / or adjust parameters through manual or voice input, it cannot guarantee that the pulse intensity controlled by the device will be adjusted to an appropriate range, resulting in a poor user experience. Summary of the Invention

[0004] This invention provides a method and system for controlling pulses in a physiotherapy device, in order to solve the technical problem in the prior art that physiotherapy devices cannot adaptively adjust different pulse controls for output.

[0005] To address the aforementioned technical problems, embodiments of the present invention provide a method for controlling pulses in a physiotherapy device, comprising: When controlling the patch to work, the detection data collected by the patch is acquired; wherein, the detection data includes: electromyography data, skin impedance, skin temperature and pressure distribution; The fit of the patch is identified based on the skin impedance and pressure distribution. After the fit is deemed satisfactory, the current working status of the physiotherapy device is determined based on the electromyography data and skin temperature. Based on the operating state category, the electrode current compensation and heating power compensation of the patch are obtained; Based on the electrode current compensation and heating power compensation, the patch adjustment current pulse and temperature are controlled.

[0006] As a preferred embodiment, acquiring the detection data collected by the patch during the control of the patch operation specifically includes: When controlling the operation of the patch, the electromyographic signal, impedance value, temperature value and pressure distribution value are collected in each preset time window through the sensor array of the patch; Based on the electromyographic signals of each preset time window, the corresponding root mean square value is calculated, and the root mean square value is used as electromyographic data. Based on the impedance value of each preset time window, the impedance change rate is calculated, and the impedance change rate is used as the skin impedance. The temperature rise rate is calculated based on the temperature value of each preset time window, and the temperature rise rate is used as the skin temperature. Based on the pressure distribution value of each preset time window, the pressure value change at each location point in the sensor array of the patch is calculated, and the pressure distribution of the patch is constructed based on the pressure value change.

[0007] As a preferred embodiment, identifying the fit of the patch based on the skin impedance and pressure distribution specifically includes: When the skin impedance is greater than a preset impedance threshold, the location point in the sensor array of the patch where the pressure value change rate is greater than a preset value is determined according to the pressure distribution, and the patch fit is generated according to the location point. When the skin impedance is not greater than a preset impedance threshold, and there is no location point in the patch sensor array where the pressure value change rate is greater than a preset value as determined by the pressure distribution, then the patch fit is satisfactory. The fit is categorized as either satisfactory or unsatisfactory.

[0008] As a preferred embodiment, generating the fit of the patch based on the location point specifically includes: When the location point exists and is located at the preset target reminder position in the patch, the adhesion of the patch is substandard. When the location point does not exist, or when the location point exists but is not at the preset target reminder position in the patch, the adhesion of the patch is considered satisfactory.

[0009] As a preferred embodiment, the operating state categories include understimulation state, ideal stimulation state, critical overstimulation state, and dangerous overstimulation state; determining the current operating state category of the physiotherapy device based on the electromyographic data and skin temperature specifically includes: When the root mean square value is less than the preset lower limit of electromyography threshold and the temperature rise rate is less than the preset lower limit of temperature rise threshold, it is determined that the current physiotherapy device is in an understimulated state. When the root mean square value is in the first electromyography threshold region between the preset lower limit and the preset upper limit of the electromyography threshold, and the temperature rise rate is in the first temperature rise threshold region between the preset lower limit and the preset upper limit of the temperature rise threshold, then the current physiotherapy device is determined to be in an ideal stimulation state. When the root mean square value is in the second electromyography threshold region between the preset lower limit and the preset upper limit of the electromyography threshold, and the temperature rise rate is in the second temperature rise threshold region between the preset lower limit and the preset upper limit of the temperature rise threshold, then the current physiotherapy device is determined to be in a critical stimulation state. When the root mean square value is greater than the preset upper limit of electromyography threshold and the temperature rise rate is greater than the preset upper limit of temperature rise threshold, the current physiotherapy device is determined to be in a dangerous stimulation state.

[0010] As a preferred embodiment, obtaining the electrode current compensation and heating power compensation of the patch based on the operating state category specifically includes: When the working state category is understimulation state, the electrode current compensation for the patch increase current is calculated based on the root mean square value of the current electromyography signal and the target electromyography signal; the heating power compensation for the patch is calculated based on the preset heating coefficient. When the operating state category is ideal stimulation state, the current electrode current and heating power remain unchanged; When the working state category is a critical stimulation state, the electrode current compensation for reducing the current of the patch is calculated based on the root mean square value of the current electromyography signal and the target electromyography signal; the heating power compensation of the patch is calculated based on the preset cooling coefficient. When the operating state category is a dangerous stimulus state, the electrode current output and heating of the patch are stopped.

[0011] As a preferred embodiment, controlling the patch adjustment current pulse and temperature based on the electrode current compensation and heating power compensation specifically includes: Based on the electrode current compensation and heating power compensation, the target current pulse and target heating power are calculated respectively. Based on the target current pulse and target heating power, the current output and heating power of the patch are controlled to adjust the current pulse and temperature of the patch.

[0012] As a preferred embodiment, after maintaining the current electrode current and heating power unchanged, the method further includes: Record the adaptation time from when the patch starts working to when the impedance change rate is less than a preset change value; The fitness score is calculated based on the impedance change rate and the adaptation time. When the fitness score is greater than the preset evaluation value, the current electrode current and heating power remain unchanged. When the fitness score is not greater than the preset evaluation value, the target electromyographic signal and the preset heating coefficient are adjusted based on the preset compensation coefficient, and the electrode current compensation and heating power compensation are recalculated based on the adjusted target electromyographic signal and the preset heating coefficient.

[0013] As a preferred embodiment, the electromyographic data further includes: the median frequency of the electromyographic signal; and prior to controlling the patch to adjust the current pulse and temperature, it further includes: When the median frequency of the electromyographic signal exceeds a preset frequency threshold, the pulse width of the current pulse adjusted by the patch is controlled based on a preset frequency reduction amplitude.

[0014] As a preferred embodiment, after controlling the patch regulating current pulse and temperature, the method further includes: Record the current current pulse and heating power, and based on the current current pulse and heating power, update the current pulse and heating power of the corresponding patch stored in the database at the time of initial operation.

[0015] As a preferred embodiment, after controlling the patch regulating current pulse and temperature, the method further includes: Collect the current and temperature parameters input by the user; An alarm is generated when both the current parameter and the temperature parameter are greater than the corresponding preset safety threshold. When both the current parameter and the temperature parameter are not greater than the corresponding preset safety threshold, a corresponding prompt sound is generated and played based on the comparison of the current parameter and the temperature parameter with the current current pulse and temperature, respectively.

[0016] As a preferred embodiment, the acquisition of the current and temperature parameters input by the user includes: The system receives current and temperature parameters input by the user through a display interaction module; or, through a voice acquisition module, it receives the user's voice control data, performs semantic analysis on the voice control data, matches current control commands and temperature control commands based on the semantic analysis results, and determines the current and temperature parameters that the user wants to adjust based on the current control commands and temperature control commands.

[0017] Accordingly, the present invention also provides a control system for a physiotherapy device pulse, comprising: a main control module and a patch connected to the main control module; The patch includes a conductive hydrogel contact layer and electrodes, heating elements and a sensing array disposed on the conductive hydrogel contact layer; The main control module is electrically connected to the electrodes, heating elements, and sensor array, and is used to implement the control method of the physiotherapy device pulse as described above.

[0018] As a preferred option, it also includes: a current control module and a temperature control module; The main control module is connected to the electrode via a current control module; the current control module is used to receive the electrode current control command generated by the main control module based on electrode current compensation, and to control and adjust the current of the electrode based on the electrode current control command. The main control module is connected to the temperature control module, and thus connected to the heating element. The temperature control module is used to receive the heating control command generated by the main control module based on the heating power compensation, and to control and adjust the heating power of the heating element based on the heating control command, so as to control the temperature of the patch.

[0019] As a preferred embodiment, it also includes: a voice acquisition module and a display interaction module; both the voice acquisition module and the display interaction module are connected to the main control module; The voice acquisition module is used to receive the user's voice data; The display interaction module is used to receive data input by the user; the user input data includes: current parameters, temperature parameters, and operating mode.

[0020] Compared with the prior art, the embodiments of the present invention have the following beneficial effects: The technical solution of this invention acquires detection data from the patch and automatically identifies the adhesion between the patch and the skin based on skin impedance and pressure distribution. Compared with traditional solutions that rely solely on fixed parameters, this method can more objectively and in real-time monitor the skin contact state. This not only effectively avoids current leakage and energy waste caused by loose adhesion, but also prevents stinging or burn risks caused by tight adhesion or changes in skin adaptability, ensuring the safety and comfort of the physiotherapy process. Furthermore, by using electromyography data and skin data to determine the current working state of the physiotherapy device, the optimal electrode current compensation and heating power compensation are dynamically calculated to control and adjust the pulse and temperature. This achieves dynamic intelligent adjustment based on individual physiological responses, ensuring that a stable and appropriate current pulse output and temperature application are obtained regardless of the user's physical condition or state. It also avoids errors in the current and heat power output of the physiotherapy device caused by users lacking professional knowledge adjusting it themselves. Thus, it can automatically adjust the current pulse and temperature parameters to suit the user when using the physiotherapy device, improving the user experience and ease of use. Attached Figure Description

[0021] Figure 1: A flowchart illustrating the steps of a method for controlling pulses in a physiotherapy device according to an embodiment of the present invention; Figure 2 : This is a schematic diagram of the control system for the physiotherapy device pulse provided in an embodiment of the present invention. Detailed Implementation

[0022] The technical solutions of the embodiments of the present invention will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only some embodiments of the present invention, and not all embodiments. Based on the embodiments of the present invention, all other embodiments obtained by those skilled in the art without creative effort are within the scope of protection of the present invention.

[0023] Example 1 Please refer to Figure 1 The present invention provides a method for controlling the pulse of a physiotherapy device, comprising the following steps S101-S105: S101: When controlling the patch to work, acquire the detection data collected by the patch; wherein, the detection data includes: electromyographic data, skin impedance, skin temperature and pressure distribution.

[0024] As a preferred embodiment, the step of acquiring the detection data collected by the patch during the control of the patch operation specifically includes: When controlling the operation of the patch, the electromyographic signal, impedance value, temperature value and pressure distribution value are collected in each preset time window through the sensor array of the patch; Based on the electromyographic signals of each preset time window, the corresponding root mean square value is calculated, and the root mean square value is used as electromyographic data. Based on the impedance value of each preset time window, the impedance change rate is calculated, and the impedance change rate is used as the skin impedance. The temperature rise rate is calculated based on the temperature value of each preset time window, and the temperature rise rate is used as the skin temperature. Based on the pressure distribution value of each preset time window, the pressure value change at each location point in the sensor array of the patch is calculated, and the pressure distribution of the patch is constructed based on the pressure value change.

[0025] In this embodiment, during the operation of the physiotherapy patch, the sensor array integrated into the patch synchronously collects electromyographic signals, impedance values, temperature values, and pressure distribution values ​​according to a preset time window, achieving real-time acquisition of multi-dimensional physiological and contact information. By using a time-segmented, window-based data acquisition method, the random errors caused by single-point sampling can be avoided, ensuring that the detection data continuously and completely reflects the interaction between the skin and the patch, as well as real-time physiological changes in the human body, providing a reliable data foundation for subsequent accurate analysis. For example, the electrode control process of the physiotherapy device can be divided into continuous time windows, preferably every 5 seconds, with electromyographic signals, impedance values, temperature values, and pressure distribution values ​​synchronously collected within each window.

[0026] It should be noted that the sensor array integrates electromyography (EMG) sensors, skin impedance sensors, temperature sensors, and pressure sensors. Before the main control module of the physiotherapy device controls the patch to work, the data detected by the sensor array is collected and used as baseline data. The baseline data includes the EMG signal, impedance value, temperature value, and pressure distribution value of the user in the resting state. After the patch is controlled to work, the detection data of the sensor array is continuously collected, that is, the EMG signal, impedance value, temperature value, and pressure distribution value after the patch applies the current pulse to the user and is heated after the physiotherapy device is working.

[0027] In this embodiment, the acquired raw signals are processed in a targeted manner to form corresponding feature data. For example, the root mean square value of the electromyographic signal is calculated to remove noise interference, reflecting the true contraction intensity and response amplitude of the muscle after stimulation; the impedance change rate is calculated for the impedance value to dynamically reflect the skin's adaptation to the current and the stability of electrode contact; and the temperature rise rate is calculated for the temperature value to accurately characterize the heating effect and the skin's thermal response state. Through the above feature calculations, the complexity of skin data can be quantified and simplified, improving the sensitivity and reliability of state judgment.

[0028] It should be noted that the root mean square value of the electromyographic (EMG) signal reflects the amplitude characteristics during the application of electrode current, while the rate of change of the median frequency of the EMG signal can quantify muscle fatigue characteristics. The rate of change of impedance reflects the process of the skin gradually adapting to the current and also reflects the degree of electrode contact with the skin.

[0029] Furthermore, in terms of pressure information processing, the overall pressure distribution of the patch is reconstructed by analyzing the pressure value changes at different locations on the sensor array within each time window. Compared to single-point pressure detection, this method can comprehensively reflect the uniformity of adhesion between the patch and the skin, accurately identify abnormal adhesion states such as local lifting, misalignment, and uneven pressure, thereby achieving a refined assessment of the patch's placement and adhesion quality, and avoiding ineffective stimulation or local discomfort caused by poor contact.

[0030] It should be noted that the pressure distribution value ensures consistent pressure contact of the patch. By calculating the standard deviation of the pressure values ​​at each point in the pressure sensor array, the degree of adhesion between the patch and the skin is quantified. When the patch exhibits abnormal adhesion conditions such as localized lifting, misalignment, or uneven pressure, for example, when lifting occurs, the pressure between the lifted portion and the skin approaches zero. The pressure is greatest at the edge of the lifted portion and the patch's contact area, decreasing towards the interior of the patch's contact area and approaching the same pressure value as the surrounding area.

[0031] In this embodiment, by combining multi-dimensional feature data with dynamic pressure distribution, the real-time status during the physiotherapy process can be identified more comprehensively and accurately. This ensures the stability and consistency of the input data and provides a quantitative basis for subsequent control strategies such as current compensation and temperature adjustment. Compared to traditional methods that rely on fixed parameters or single signals, the data processing logic in this embodiment is more in line with the physiological changes of the human body, effectively improving the accuracy of status identification and its anti-interference capability.

[0032] In this embodiment, the layered data acquisition and feature calculation method of the sensor array improves the detection accuracy and enhances the system's adaptability to different usage scenarios and individual differences. This lays the foundation for adaptive adjustment of physiotherapy parameters, thereby making current stimulation and temperature control more precise and stable. It not only improves the physiotherapy effect and user comfort, but also reduces the safety risks caused by abnormal fit or unsuitable parameters, and improves the reliability and intelligence level of the equipment operation.

[0033] S102: Identify the fit of the patch based on the skin impedance and pressure distribution.

[0034] As a preferred embodiment, identifying the fit of the patch based on the skin impedance and pressure distribution specifically includes: When the skin impedance is greater than a preset impedance threshold, the location point in the sensor array of the patch where the pressure value change rate is greater than a preset value is determined according to the pressure distribution, and the patch fit is generated according to the location point. When the skin impedance is not greater than a preset impedance threshold, and there is no location point in the patch sensor array where the pressure value change rate is greater than a preset value as determined by the pressure distribution, then the patch fit is satisfactory. The fit is categorized as either satisfactory or unsatisfactory.

[0035] In this embodiment, a preset impedance threshold is set as a judgment criterion. During the operation of the physiotherapy patch, the skin impedance is monitored and graded in real time. When the detected skin impedance is greater than the preset impedance threshold, it is determined that the current contact state between the electrode and the skin is abnormal. Then, further analysis is carried out in combination with pressure distribution data to achieve preliminary screening and rapid identification of the patch adhesion state, providing clear triggering conditions for subsequent refined detection.

[0036] In this embodiment, when the skin impedance exceeds a threshold, abnormal locations in the sensor array with pressure change rates exceeding preset values ​​are further identified based on pressure distribution information. By quantifying and comparing the pressure change rates, abnormal areas such as localized patch lifting, offset, wrinkling, or loose contact can be accurately located, avoiding misjudgments caused by relying solely on the overall pressure average, thereby improving the accuracy and specificity of identifying abnormal adhesion locations. It is understood that the preset impedance threshold and preset values ​​can be set according to actual needs.

[0037] In this embodiment, based on the identified abnormal location points, a comprehensive result for the patch's fit is generated, and the fit is clearly divided into two categories: acceptable and unacceptable. A preferred embodiment is shown below.

[0038] In a preferred embodiment, generating the fit of the patch based on the location point specifically includes: When the location point exists and is located at the preset target reminder position in the patch, the adhesion of the patch is substandard. When the location point does not exist, or when the location point exists but is not at the preset target reminder position in the patch, the adhesion of the patch is considered satisfactory.

[0039] In this embodiment, by locating the position points, it is ensured that the points with large pressure change rates on the patch are in critical positions, such as the center of the electrode. If an abnormal position point is located at the center of the electrode, it indicates that the electrode is not adhering well to the skin. For other non-preset target positions, such as the edge of the patch, the skin may stretch due to joint movement, causing the patch edge to loosen, but this does not affect the electrode's output current pulse, so no warning is needed for this position. Therefore, the patch's fit is considered satisfactory. By combining the dual dimensions of skin impedance and pressure distribution, the limitations of judging by a single parameter are eliminated, which can more comprehensively and objectively reflect the actual contact quality between the patch and the skin, effectively improving the reliability of the fit evaluation results.

[0040] In this embodiment, when the skin impedance is not greater than a preset impedance threshold and no location with an excessive rate of pressure change is detected in the pressure distribution, the patch fit is directly determined to be satisfactory. This judgment logic simplifies the calculation process in satisfactory scenarios, improves system operating efficiency while ensuring judgment accuracy, and avoids unnecessary data analysis and instruction calculations, thereby reducing device power consumption and processing latency.

[0041] Understandably, the graded fit assessment scheme, by combining impedance threshold screening with pressure change rate detection, achieves efficient and accurate identification of the patch's fit status, promptly eliminating factors such as poor contact that could affect therapeutic efficacy and safety. Through standardized judgment logic, it not only improves the stability of the physiotherapy device's initial operating state but also provides a reliable foundation for subsequent adaptive control such as current adjustment and temperature compensation, effectively ensuring the safety, comfort, and effectiveness of the physiotherapy device's control process.

[0042] S103: After the fit is deemed satisfactory, the current working status category of the physiotherapy device is determined based on the electromyography data and skin temperature.

[0043] As a preferred embodiment, the working state categories include understimulation state, ideal stimulation state, critical overstimulation state, and dangerous overstimulation state; determining the current working state category of the physiotherapy device based on the electromyography data and skin temperature specifically includes: When the root mean square value is less than the preset lower limit of electromyography threshold and the temperature rise rate is less than the preset lower limit of temperature rise threshold, it is determined that the current physiotherapy device is in an understimulated state. When the root mean square value is in the first electromyography threshold region between the preset lower limit and the preset upper limit of the electromyography threshold, and the temperature rise rate is in the first temperature rise threshold region between the preset lower limit and the preset upper limit of the temperature rise threshold, then the current physiotherapy device is determined to be in an ideal stimulation state. When the root mean square value is in the second electromyography threshold region between the preset lower limit and the preset upper limit of the electromyography threshold, and the temperature rise rate is in the second temperature rise threshold region between the preset lower limit and the preset upper limit of the temperature rise threshold, then the current physiotherapy device is determined to be in a critical stimulation state. When the root mean square value is greater than the preset upper limit of electromyography threshold and the temperature rise rate is greater than the preset upper limit of temperature rise threshold, the current physiotherapy device is determined to be in a dangerous stimulation state.

[0044] In this embodiment, the root mean square value of electromyography (EMG) signal and the rate of skin temperature rise are used as the core judgment indicators. By presetting multiple sets of thresholds and threshold regions, the stimulation state of the physiotherapy device can be accurately classified and identified. It should be noted that the judgment criteria for the two types of core detection parameters need to be clearly defined. The root mean square value of EMG signal corresponds to the degree of excitation of the muscle after stimulation, and the rate of temperature rise corresponds to the thermal response state of the skin to the physiotherapy heating. By judging the two parameters in tandem, the limitations of judging by a single parameter are avoided, and a scientific basis is provided for the accurate differentiation of stimulation states.

[0045] In this embodiment, a clear determination logic is set for the understimulation state: when the root mean square value of the electromyography (EMG) signal is lower than a preset lower limit of the EMG threshold, and the skin temperature rise rate is lower than a preset lower limit of the temperature rise threshold, the physiotherapy device is determined to be in an understimulation state. This determination logic corresponds to the core characteristics of insufficient muscle stimulation and insignificant heating effect. Through the dual constraint that both parameters are below the threshold, misjudgment caused by a single parameter abnormality is avoided, ensuring the accuracy of understimulation state identification and providing a clear trigger condition for subsequent parameter compensation.

[0046] In this embodiment, the ideal stimulation state and the critical stimulation state are finely distinguished. Both are determined based on the root mean square value of the electromyographic signal and the rate of temperature rise falling within corresponding preset threshold ranges. Furthermore, by dividing the system into a first threshold region and a second threshold region, the two qualified states are precisely defined. The ideal stimulation state corresponds to both parameters being within the optimal threshold range, ensuring a balance between therapeutic effect and user comfort. The critical stimulation state corresponds to both parameters being within the qualified range but close to the threshold boundary, providing a warning signal to the system and preventing the stimulation intensity from shifting towards dangerous or understimulated directions.

[0047] In this embodiment, strict judgment conditions are set for dangerous stimuli: when the root mean square value of the electromyography (EMG) signal is higher than the upper limit of the preset EMG threshold, and the skin temperature rise rate is higher than the upper limit of the preset temperature rise threshold, it is judged as a dangerous stimuli. This dual upper limit constraint can accurately identify dangerous scenarios of muscle over-excitation and skin overheating, promptly capture abnormal states that may cause user discomfort or even skin damage, provide a reliable basis for emergency system adjustments, and ensure the safety of the physiotherapy process.

[0048] For example, the physical therapy status can be determined based on the root mean square (RMS) value of the electromyographic signal and the skin temperature rise rate (dT / dt) of the temperature response characteristics, as shown in Table 1 below: Table 1. Comparison Table of Root Mean Square Value of Electromyographic Signal and Skin Temperature Rise Rate It should be noted that the threshold selection for the above judgment can be obtained based on benchmark data and statistical models of similar populations. That is, the preset lower limit and upper limit of electromyography threshold, the preset lower limit and upper limit of temperature rise threshold, as well as the first electromyography threshold region and the second electromyography threshold region, the first temperature rise threshold region and the second temperature rise threshold region can be obtained based on benchmark data and statistical models of similar populations, or can be set based on expert experience and actual needs.

[0049] Understandably, by employing dual-parameter collaborative judgment and multi-state refined classification, comprehensive and accurate identification of the stimulation state of the physiotherapy device is achieved. This avoids the one-sidedness of single-parameter judgment and solves the problem of ambiguous state classification in traditional methods. It can provide real-time feedback on the actual effect of the physiotherapy stimulation, providing precise state support for subsequent electrode current compensation and heating power compensation. This ensures that the physiotherapy process achieves ideal therapeutic effects while effectively avoiding poor results due to understimulation and safety hazards caused by dangerous stimulation. Furthermore, through critical state warnings, it enhances the system's adaptive adjustment capabilities, improving the reliability of equipment operation and the safety and comfort of user operation.

[0050] S104: Based on the operating state category, obtain the electrode current compensation and heating power compensation of the patch.

[0051] As a preferred embodiment, the step of obtaining the electrode current compensation and heating power compensation of the patch according to the working state category specifically includes: When the working state category is understimulation state, the electrode current compensation for the patch increase current is calculated based on the root mean square value of the current electromyography signal and the target electromyography signal; the heating power compensation for the patch is calculated based on the preset heating coefficient. When the operating state category is ideal stimulation state, the current electrode current and heating power remain unchanged; When the working state category is a critical stimulation state, the electrode current compensation for reducing the current of the patch is calculated based on the root mean square value of the current electromyography signal and the target electromyography signal; the heating power compensation of the patch is calculated based on the preset cooling coefficient. When the operating state category is a dangerous stimulus state, the electrode current output and heating of the patch are stopped.

[0052] In this embodiment, a targeted electrode current and heating power control strategy was developed based on different operating states of the physiotherapy device to achieve adaptive adjustment of the physiotherapy parameters. Specifically, the root mean square value of the electromyography signal, the target electromyography signal, and the preset heating coefficient / preset cooling coefficient were used as the core calculation basis. Combined with the characteristics of four states—understimulation, ideal stimulation, critical stimulation, and dangerous stimulation—differentiated control logic was constructed to ensure the accuracy and rationality of the physiotherapy device parameter adjustment.

[0053] In this embodiment, when the physiotherapy device is determined to be in an understimulation state, a parameter enhancement compensation mechanism is activated. For the electrode current, based on the current root mean square value of the electromyography (EMG) signal and combined with a preset target EMG signal, the electrode current compensation amount is obtained through quantitative calculation. This compensation increases the patch output current to compensate for insufficient muscle stimulation. For the heating power, a corresponding heating power compensation amount is calculated based on a preset temperature rise coefficient to improve the heating effect. This allows the controlled current and temperature parameters to quickly approach the ideal range, effectively improving the poor results caused by understimulation.

[0054] In this embodiment, when the physiotherapy device is in an ideal stimulation state, the system adopts a maintenance control strategy to keep the current electrode current and heating power stable. Based on the characteristic that both parameters (electromyographic signal and temperature rise rate) are in the optimal threshold range under ideal stimulation state, unnecessary parameter adjustments are avoided. This reduces the system's computational load and device power consumption, while maintaining a stable physiotherapy effect and a comfortable user experience, achieving stability and efficiency in the physiotherapy process.

[0055] In this embodiment, for critical stimulation states, a parameter reduction compensation mechanism is activated to prevent the stimulation intensity from shifting towards a dangerous area. Regarding electrode current control, the electrode current compensation amount is calculated by combining the current root mean square value of the electromyography (EMG) signal with the target EMG signal, thus appropriately reducing the muscle stimulation intensity. Regarding heating power control, the heating power compensation amount is calculated based on a preset cooling coefficient to reduce the heating intensity, bringing the parameters back to the ideal range. Through early warning and fine-tuning, the safety and stability of the physiotherapy device are ensured.

[0056] In this embodiment, when a dangerous stimulus is detected, an emergency shutdown control is executed, immediately stopping the electrode current output and heating function of the patch. Based on the risk characteristics of electromyographic signals and temperature rise rates exceeding safety thresholds under dangerous stimulus conditions, quickly cutting off the stimulus source effectively avoids user discomfort and skin damage caused by excessive muscle excitation and skin overheating, maximizing user safety. It is understood that the differentiated control scheme achieves adaptive adjustment of physiotherapy parameters and risk control, improving the stability of the physiotherapy device and enhancing the safety and reliability of equipment operation, adapting to the needs of different users.

[0057] For example, the current intensity and temperature can be adjusted according to different operating conditions: For the understimulated state: I_new = I + ΔI, P_new = P_current × (1 + 0.3) Where I_new is the target current after compensation, I is the current electrode current, ΔI is the electrode current compensation, P_new is the target heating efficiency after compensation, P_current is the current heating efficiency, and the preset heating coefficient can preferably be set to 0.3.

[0058] For an ideal stimulus state: maintain the current current and temperature constant.

[0059] Critical overexcitation state: I_new = I-ΔI, P_new = P_current × (1-0.3) Where I_new is the target current after compensation, I is the current electrode current, ΔI is the electrode current compensation, P_new is the target heating efficiency after compensation, P_current is the current heating efficiency, and the preset cooling coefficient can preferably be set to 0.3.

[0060] In case of dangerous or extreme conditions: immediately stop current output and heating operation (safety interruption).

[0061] As another preferred embodiment, after keeping the current electrode current and heating power unchanged, the method further includes: Record the adaptation time from when the patch starts working to when the impedance change rate is less than a preset change value; The fitness score is calculated based on the impedance change rate and the adaptation time. When the fitness score is greater than the preset evaluation value, the current electrode current and heating power remain unchanged. When the fitness score is not greater than the preset evaluation value, the target electromyographic signal and the preset heating coefficient are adjusted based on the preset compensation coefficient, and the electrode current compensation and heating power compensation are recalculated based on the adjusted target electromyographic signal and the preset heating coefficient.

[0062] In this embodiment, by recording the adaptation time from the start-up of the physiotherapy patch to the impedance change rate falling below a preset value, and combining this with the real-time impedance change rate to calculate an adaptation score, a quantitative assessment of the skin's current adaptation process is achieved. Transforming the skin's dynamic adaptation characteristics into a calculable and comparable scoring index objectively reflects the stability of the electrode-skin interface, providing a dynamic basis for the fine-tuning of the physiotherapy device's control parameters. This avoids deviations in stimulation effects caused by individual skin differences and varying adaptation states, improving the scientific rigor and accuracy of the state assessment.

[0063] It should be noted that in the initial stage of current stimulation, skin impedance is high and fluctuates greatly. As the skin gradually adapts to the current stimulation, changes in the stratum corneum, local microcirculation, and electrode contact become more stable, and the impedance gradually decreases and tends to stabilize. By calculating the impedance decrease magnitude, impedance fluctuation variance, and the time required for impedance to stabilize, the degree and speed of skin adaptation can be quantitatively assessed, thus achieving an objective characterization of the skin's adaptation process to the current. Therefore, by using the impedance change rate, i.e., the impedance decrease magnitude, to characterize the degree of adaptation, and using the time for impedance to stabilize to assess the speed of adaptation, an adaptation score can be calculated. S = k 1 ⋅R d + k 2 ⋅1 / T s in, S It is a fitness score. R d For impedance decrease rate, T s To adapt to time, k 1 and k 2 These are the weighting coefficients. The weighting coefficients can be set according to actual needs.

[0064] Understandably, based on the comparison between the fitness score and the preset evaluation value, the control parameters of the physiotherapy device can be adaptively adjusted: when the fitness score meets the standard, the current output remains stable, ensuring a continuous and smooth physiotherapy process; when the score does not meet the standard, the target electromyographic signal and heating coefficient are dynamically corrected through a preset compensation coefficient, and the electrode current compensation and heating power compensation are recalculated iteratively to make the output current of the physiotherapy device more closely match the user's actual skin adaptation characteristics. This effectively solves the problem that fixed parameters are difficult to adapt to dynamic changes in the skin, further improving the accuracy of current intensity and heating effect, enhancing the device's adaptability to different users and different usage conditions, and improving the effectiveness and safety of the output current pulses of the physiotherapy device while optimizing the user experience.

[0065] S105: Based on the electrode current compensation and heating power compensation, control the patch adjustment current pulse and temperature.

[0066] As a preferred embodiment, the step of controlling the patch adjustment current pulse and temperature based on the electrode current compensation and heating power compensation specifically includes: Based on the electrode current compensation and heating power compensation, the target current pulse and target heating power are calculated respectively. Based on the target current pulse and target heating power, the current output and heating power of the patch are controlled to adjust the current pulse and temperature of the patch.

[0067] In this embodiment, after obtaining electrode current compensation and heating power compensation, the compensation amounts are further converted into directly executable control parameters, i.e., the target current pulse and target heating power are obtained through quantization calculations. This process is based on compensation logic corresponding to different operating state categories, ensuring that the target parameters are accurately matched with the compensation requirements of understimulation, critical stimulation, and other states. It also takes into account both the maintenance control of ideal stimulation states and the shutdown control of dangerous stimulation states, achieving an orderly conversion of compensation amounts into actual control commands and ensuring the coherence of the control logic and the accuracy of parameter calculations.

[0068] In this embodiment, the calculated target current pulse and target heating power are used as the control basis to precisely regulate the current output and heating power of the patch, thereby achieving dynamic adjustment of the patch current pulse intensity and temperature. This control method forms a closed loop between state determination, compensation calculation, and actual execution, ensuring that the patch output always adapts to the user's skin adaptation state and muscle stimulation needs. Specifically, it can precisely increase parameters during understimulation and appropriately decrease parameters during critical stimulation, maintain stability under ideal conditions, and shut down in emergency situations, effectively ensuring the stability of the therapeutic effect and the safety of use. Simultaneously, it simplifies the control chain, improves response efficiency, enhances the reliability and intelligence of the equipment, and adapts to the individual differences and needs of different users.

[0069] As a preferred embodiment, the electromyographic data further includes: the median frequency of the electromyographic signal; and before controlling the patch to adjust the current pulse and temperature, it further includes: When the median frequency of the electromyographic signal exceeds a preset frequency threshold, the pulse width of the current pulse adjusted by the patch is controlled based on a preset frequency reduction amplitude.

[0070] In this embodiment, the median frequency of the electromyographic signal is detected in real time. When the median frequency exceeds a preset frequency threshold, the pulse width of the current pulse after patch adjustment is precisely controlled based on a preset frequency reduction amplitude. It should be noted that the median frequency of the electromyographic signal is used as the core monitoring indicator to reflect the abnormal state of muscle excitation. By standardizing the pulse width adjustment amplitude through a preset frequency reduction amplitude, the adjustment process is ensured to be smooth and controllable, avoiding excessive stimulation or discomfort to the muscle caused by sudden pulse width changes, and achieving fine supplementary control of the current pulse parameters.

[0071] As a preferred embodiment, after controlling the patch adjustment current pulse and temperature, the method further includes: Record the current current pulse and heating power, and based on the current current pulse and heating power, update the current pulse and heating power of the corresponding patch stored in the database at the time of initial operation.

[0072] In this embodiment, the current pulse parameters and heating power parameters output by the patch during the physiotherapy process are recorded in real time, and the current pulse and heating power parameters corresponding to the initial working stage of the patch stored in the database are dynamically updated to achieve closed-loop storage and iterative optimization of operating parameters. By synchronously updating the effective operating parameters output in real time to the database, personalized control data adapted to the user's physiological characteristics and skin adaptation status can be continuously accumulated. This allows the device to directly call up initial parameters that are more in line with actual needs when starting up or reusing it in subsequent applications, effectively shortening the adjustment cycle of the physiotherapy device in the early stage, improving parameter matching accuracy and control stability, and providing a continuously optimized data foundation for the intelligent adaptive control of the physiotherapy device, further enhancing the device's adaptability to different usage scenarios and individual differences.

[0073] Implementing the above embodiments has the following effects: The technical solution of this invention acquires detection data from the patch and automatically identifies the adhesion between the patch and the skin based on skin impedance and pressure distribution. Compared with traditional solutions that rely solely on fixed parameters, this method can more objectively and in real-time monitor the skin contact state. This not only effectively avoids current leakage and energy waste caused by loose adhesion, but also prevents stinging or burn risks caused by tight adhesion or changes in skin adaptability, ensuring the safety and comfort of the physiotherapy process. Furthermore, by using electromyography data and skin data to determine the current working state of the physiotherapy device, the optimal electrode current compensation and heating power compensation are dynamically calculated to control and adjust the pulse and temperature. This achieves dynamic intelligent adjustment based on individual physiological responses, ensuring that a stable and appropriate current pulse output and temperature application are obtained regardless of the user's physical condition or state. It also avoids errors in the current and heat power output of the physiotherapy device caused by users lacking professional knowledge adjusting it themselves. Thus, it can automatically adjust the current pulse and temperature parameters to suit the user when using the physiotherapy device, improving the user experience and ease of use.

[0074] Example 2 The present invention also provides several preferred embodiments of the control method for the pulse of the physiotherapy device, as follows: As a preferred embodiment, after controlling the patch adjustment current pulse and temperature, the method further includes: Collect the current and temperature parameters input by the user; An alarm is generated when both the current parameter and the temperature parameter are greater than the corresponding preset safety threshold. When both the current parameter and the temperature parameter are not greater than the corresponding preset safety threshold, a corresponding prompt sound is generated and played based on the comparison of the current parameter and the temperature parameter with the current current pulse and temperature, respectively.

[0075] In this embodiment, user-inputted current and temperature parameters are collected and incorporated into the system control process. This satisfies users' personalized adjustment needs for therapeutic intensity and provides a data foundation for subsequent safety verification and status prompts, achieving an organic combination of user-independent operation and intelligent equipment management. After acquiring the user-input parameters, the system compares them with preset safety thresholds. When both current and temperature parameters exceed the corresponding safety thresholds, an alarm signal is immediately generated. This proactive warning mechanism effectively avoids safety risks such as excessive current or temperature caused by improper user settings, improving the safety and reliability of the equipment. If the user-input current and temperature parameters are within the safety threshold range, the system further compares these parameters with the current pulse and temperature currently output by the patch in real time, and generates and plays corresponding prompt sounds based on the comparison results, providing intuitive feedback on parameter differences and adjustment status. This improves the smoothness of human-computer interaction while ensuring safety, allowing users to clearly perceive parameter matching and enhancing operational controllability and user experience.

[0076] As a preferred embodiment, the acquisition of the current and temperature parameters input by the user includes: The system receives current and temperature parameters input by the user through a display interaction module; or, through a voice acquisition module, it receives the user's voice control data, performs semantic analysis on the voice control data, matches current control commands and temperature control commands based on the semantic analysis results, and determines the current and temperature parameters that the user wants to adjust based on the current control commands and temperature control commands.

[0077] In this embodiment, the current and temperature parameters input by the user can be directly received through the display interaction module, or the user's voice control data can be acquired through the voice acquisition module. After semantic analysis, the corresponding current and temperature control commands are matched to determine the current and temperature parameters that the user wishes to adjust. This approach combines both touch and voice interaction control modes, broadening the user's operation path, adapting to different usage scenarios and operating habits, and improving the convenience and intelligence of device operation.

[0078] It should be noted that obtaining user adjustment intentions through multimodal interaction can reduce the complexity of user operation while ensuring the accuracy of parameter input, thus achieving high efficiency and user-friendliness in human-computer interaction. Combining the precision of touch input with the convenience of voice control can meet the adjustment needs of users in different usage postures, making the setting of physiotherapy parameters more flexible and efficient, and further improving the overall user experience and ease of use of the equipment.

[0079] For example, during the operation of the physiotherapy device, the user may feel that the stimulation is insufficient, and thus actively adjust the current and temperature parameters through the display interaction module, or input voice control data through the voice acquisition module. If it is voice control data, it is converted into voice control text, and the voice control text and a simplified instruction set are input into the corresponding artificial intelligence semantic recognition model for instruction matching. For example, if the user inputs "the current stimulation is too strong," the corresponding matching instruction is "reduce the current intensity." However, the user's active adjustment may conflict with the parameters determined by the adaptive algorithm in Example 1, requiring a corresponding priority conflict resolution strategy, i.e., determining the user's adjustment... If the parameters of the section exceed the safety limit, the user adjustment is ignored and a warning voice prompt is generated. If, after comparing the user-adjusted parameters with the optimal ideal parameters, it is found that the user-adjusted parameters may reduce the therapeutic effect or cause damage to the body (e.g., lowering the current leads to insufficient stimulation, raising the temperature leads to low-temperature burns, etc.), a suggested voice prompt is generated based on the comparison results (e.g., "The current skin temperature is already high. Increasing the temperature further may cause discomfort or burns. Please confirm whether you want to continue increasing the temperature."). After the suggested voice prompt is played, if the user clicks "Confirm" in the display interaction module, the program will work according to the user's adjusted parameters. If the user clicks "Cancel," the user adjustment is ignored.

[0080] Example 3 Accordingly, the present invention also provides a control system for a physiotherapy device pulse, comprising: a main control module and a patch connected to the main control module.

[0081] The patch includes a conductive hydrogel contact layer and electrodes, heating elements and a sensing array disposed on the conductive hydrogel contact layer.

[0082] The main control module is electrically connected to the electrodes, heating elements, and sensor array, and is used to implement the control method of the physiotherapy device pulse as described above.

[0083] As a preferred option, it also includes: a current control module and a temperature control module; The main control module is connected to the electrode via a current control module; the current control module is used to receive the electrode current control command generated by the main control module based on electrode current compensation, and to control and adjust the current of the electrode based on the electrode current control command. The main control module is connected to the temperature control module, and thus connected to the heating element. The temperature control module is used to receive the heating control command generated by the main control module based on the heating power compensation, and to control and adjust the heating power of the heating element based on the heating control command, so as to control the temperature of the patch.

[0084] In this embodiment, the control system for the physiotherapy device's pulses includes a main control module, a current control module, a temperature control module, a voice acquisition module, a display and interaction module, a storage module, a power management module, and a patch integrating electrodes, heating elements, a sensor array, and a conductive gel contact layer. Multiple patches can be used. The main control module, current control module, and temperature control module are connected to each patch via multi-channel input / output ports. The main control module determines the port corresponding to the currently used patch through the display and interaction module and controls the corresponding patch through that port. The storage module stores a database, and the power management module manages the charging of the physiotherapy device.

[0085] It should be noted that the sensor array includes electromyography (EMG) sensors, skin impedance sensors, temperature sensors, and pressure sensors. After the user inputs a start command or mode selection command through the display interaction module, the system retrieves the database from the storage unit. Based on the mode selection command, it determines the corresponding smart therapy patch and the initial operating parameters from the database, including current and temperature parameters. The main control module then collects the sensor array's detection data as baseline data, which includes the user's resting EMG noise level, initial skin impedance, and initial skin temperature. After acquiring the baseline data, the main control module sends the current parameters to the current control module and the temperature parameters to the temperature control module. The current control module drives the therapy electrodes to discharge based on the current parameters, and the temperature control module drives the heating element to operate based on the temperature parameters.

[0086] As a preferred embodiment, it also includes: a voice acquisition module and a display interaction module; both the voice acquisition module and the display interaction module are connected to the main control module; The voice acquisition module is used to receive the user's voice data; The display interaction module is used to receive data input by the user; the user input data includes: current parameters, temperature parameters, and operating mode.

[0087] In this embodiment, the user's voice control data is acquired through the voice acquisition module, and after semantic analysis, the corresponding current and temperature control commands are matched to determine the current and temperature parameters that the user wishes to adjust.

[0088] For example, during the operation of the physiotherapy device, the user may feel that the stimulation is insufficient, and thus actively adjust the current and temperature parameters through the display interaction module, or input voice control data through the voice acquisition module. If it is voice control data, it is converted into voice control text, and the voice control text and a simplified instruction set are input into the corresponding artificial intelligence semantic recognition model for instruction matching. For example, if the user inputs "the current stimulation is too strong," the corresponding matching instruction is "reduce the current intensity." However, the user's active adjustment may conflict with the parameters determined by the adaptive algorithm in Example 1, requiring a corresponding priority conflict resolution strategy, i.e., determining the user's adjustment... If the parameters of the section exceed the safety limit, the user adjustment is ignored and a warning voice prompt is generated. If, after comparing the user-adjusted parameters with the optimal ideal parameters, it is found that the user-adjusted parameters may reduce the therapeutic effect or cause damage to the body (e.g., lowering the current leads to insufficient stimulation, raising the temperature leads to low-temperature burns, etc.), a suggested voice prompt is generated based on the comparison results (e.g., "The current skin temperature is already high. Increasing the temperature further may cause discomfort or burns. Please confirm whether you want to continue increasing the temperature."). After the suggested voice prompt is played, if the user clicks "Confirm" in the display interaction module, the program will work according to the user's adjusted parameters. If the user clicks "Cancel," the user adjustment is ignored.

[0089] Those skilled in the art will understand that, for the sake of convenience and brevity, the specific working process of the modules described above can be referred to the corresponding process in the foregoing method embodiments, and will not be repeated here.

[0090] Implementing the above embodiments has the following effects: The technical solution of this invention acquires detection data from the patch and automatically identifies the adhesion between the patch and the skin based on skin impedance and pressure distribution. Compared with traditional solutions that rely solely on fixed parameters, this method can more objectively and in real-time monitor the skin contact state. This not only effectively avoids current leakage and energy waste caused by loose adhesion, but also prevents stinging or burn risks caused by tight adhesion or changes in skin adaptability, ensuring the safety and comfort of the physiotherapy process. Furthermore, by using electromyography data and skin data to determine the current working state of the physiotherapy device, the optimal electrode current compensation and heating power compensation are dynamically calculated to control and adjust the pulse and temperature. This achieves dynamic intelligent adjustment based on individual physiological responses, ensuring that a stable and appropriate current pulse output and temperature application are obtained regardless of the user's physical condition or state. It also avoids errors in the current and heat power output of the physiotherapy device caused by users lacking professional knowledge adjusting it themselves. Thus, it can automatically adjust the current pulse and temperature parameters to suit the user when using the physiotherapy device, improving the user experience and ease of use.

[0091] Example 4 Accordingly, the present invention also provides a terminal device, comprising: a processor, a memory, and a computer program stored in the memory and configured to be executed by the processor, wherein the processor executes the computer program to implement the control method for physiotherapy pulses as described in any of the above embodiments.

[0092] The terminal device in this embodiment includes a processor, a memory, and a computer program and computer instructions stored in the memory and executable on the processor. When the processor executes the computer program, it implements the various steps described in Embodiment 1 above, for example... Figure 1 The steps S101 to S105 are shown. Alternatively, when the processor executes the computer program, it implements the functions of each module / unit in the above-described device embodiment.

[0093] For example, the computer program may be divided into one or more modules / units, which are stored in the memory and executed by the processor to complete the present invention. The one or more modules / units may be a series of computer program instruction segments capable of performing a specific function, which describe the execution process of the computer program in the terminal device.

[0094] The terminal device may be a desktop computer, laptop, handheld computer, or cloud server, etc. The terminal device may include, but is not limited to, a processor and memory. Those skilled in the art will understand that the schematic diagram is merely an example of a terminal device and does not constitute a limitation on the terminal device. It may include more or fewer components than illustrated, or combine certain components, or different components. For example, the terminal device may also include input / output devices, network access devices, buses, etc.

[0095] The processor can be a Central Processing Unit (CPU), or other general-purpose processors, digital signal processors (DSPs), application-specific integrated circuits (ASICs), field-programmable gate arrays (FPGAs), or other programmable logic devices, discrete gate or transistor logic devices, discrete hardware components, etc. A general-purpose processor can be a microprocessor or any conventional processor. The processor is the control center of the terminal device, connecting all parts of the terminal device via various interfaces and lines.

[0096] The memory can be used to store the computer programs and / or modules. The processor implements various functions of the terminal device by running or executing the computer programs and / or modules stored in the memory and by calling data stored in the memory. The memory may mainly include a program storage area and a data storage area. The program storage area may store the operating system, applications required for at least one function, etc.; the data storage area may store data created based on the use of the mobile terminal, etc. In addition, the memory may include high-speed random access memory, and may also include non-volatile memory, such as hard disk, RAM, plug-in hard disk, smart media card (SMC), secure digital card (SD card), flash card, at least one disk storage device, flash memory device, or other volatile solid-state storage device.

[0097] Wherein, if the modules / units integrated in the terminal device are implemented as software functional units and sold or used as independent products, they can be stored in a computer-readable storage medium. Based on this understanding, all or part of the processes in the methods of the above embodiments of the present invention can also be implemented by a computer program instructing related hardware. The computer program can be stored in a computer-readable storage medium, and when the computer program is executed by a processor, it can implement the steps of the various method embodiments described above. Wherein, the computer program includes computer program code, which can be in the form of source code, object code, executable file, or some intermediate form, etc. The computer-readable medium can include: any entity or device capable of carrying the computer program code, recording medium, USB flash drive, portable hard drive, magnetic disk, optical disk, computer memory, read-only memory (ROM), random access memory (RAM), electrical carrier signals, telecommunication signals, and software distribution media, etc. It should be noted that the content contained in the computer-readable medium can be appropriately added or removed according to the requirements of legislation and patent practice in the jurisdiction. For example, in some jurisdictions, according to legislation and patent practice, the computer-readable medium does not include electrical carrier signals and telecommunication signals.

[0098] Example 5 Accordingly, the present invention also provides a computer-readable storage medium comprising a stored computer program, wherein, when the computer program is executed, it controls the device containing the computer-readable storage medium to perform the control method for physiotherapy pulses as described in any of the above embodiments.

[0099] The specific embodiments described above further illustrate the purpose, technical solution, and beneficial effects of the present invention. It should be understood that the above descriptions are merely specific embodiments of the present invention and are not intended to limit the scope of protection of the present invention. In particular, it should be noted that any modifications, equivalent substitutions, improvements, etc., made within the spirit and principles of the present invention should be included within the scope of protection of the present invention for those skilled in the art.

Claims

1. A method for controlling pulses in a physiotherapy device, characterized in that, include: When controlling the patch to work, the detection data collected by the patch is acquired; wherein, the detection data includes: electromyography data, skin impedance, skin temperature and pressure distribution; The fit of the patch is identified based on the skin impedance and pressure distribution. After the fit is deemed satisfactory, the current working status of the physiotherapy device is determined based on the electromyography data and skin temperature. Based on the operating state category, the electrode current compensation and heating power compensation of the patch are obtained; Based on the electrode current compensation and heating power compensation, the patch adjustment current pulse and temperature are controlled.

2. The method for controlling pulses in a physiotherapy device as described in claim 1, characterized in that, The process of acquiring the detection data collected by the patch during control of patch operation specifically includes: When controlling the operation of the patch, the electromyographic signal, impedance value, temperature value and pressure distribution value are collected in each preset time window through the sensor array of the patch; Based on the electromyographic signals of each preset time window, the corresponding root mean square value is calculated, and the root mean square value is used as electromyographic data. Based on the impedance value of each preset time window, the impedance change rate is calculated, and the impedance change rate is used as the skin impedance. The temperature rise rate is calculated based on the temperature value of each preset time window, and the temperature rise rate is used as the skin temperature. Based on the pressure distribution value of each preset time window, the pressure value change at each location point in the sensor array of the patch is calculated, and the pressure distribution of the patch is constructed based on the pressure value change.

3. The method for controlling pulses in a physiotherapy device as described in claim 2, characterized in that, The step of identifying the fit of the patch based on the skin impedance and pressure distribution specifically includes: When the skin impedance is greater than a preset impedance threshold, the location point in the sensor array of the patch where the pressure value change rate is greater than a preset value is determined according to the pressure distribution, and the patch fit is generated according to the location point. When the skin impedance is not greater than a preset impedance threshold, and there is no location point in the patch sensor array where the pressure value change rate is greater than a preset value as determined by the pressure distribution, then the patch fit is satisfactory. The fit is categorized as either satisfactory or unsatisfactory.

4. The method for controlling pulses in a physiotherapy device as described in claim 3, characterized in that, The step of generating the fit of the patch based on the location point specifically includes: When the location point exists and is located at the preset target reminder position in the patch, the adhesion of the patch is substandard. When the location point does not exist, or when the location point exists but is not at the preset target reminder position in the patch, the adhesion of the patch is considered satisfactory.

5. The method for controlling pulses in a physiotherapy device as described in claim 2, characterized in that, The operating state categories include understimulation state, ideal stimulation state, critical overstimulation state, and dangerous overstimulation state; determining the current operating state category of the physiotherapy device based on the electromyographic data and skin temperature specifically includes: When the root mean square value is less than the preset lower limit of electromyography threshold and the temperature rise rate is less than the preset lower limit of temperature rise threshold, it is determined that the current physiotherapy device is in an understimulated state. When the root mean square value is in the first electromyography threshold region between the preset lower limit and the preset upper limit of the electromyography threshold, and the temperature rise rate is in the first temperature rise threshold region between the preset lower limit and the preset upper limit of the temperature rise threshold, then the current physiotherapy device is determined to be in an ideal stimulation state. When the root mean square value is in the second electromyography threshold region between the preset lower limit and the preset upper limit of the electromyography threshold, and the temperature rise rate is in the second temperature rise threshold region between the preset lower limit and the preset upper limit of the temperature rise threshold, then the current physiotherapy device is determined to be in a critical stimulation state. When the root mean square value is greater than the preset upper limit of electromyography threshold and the temperature rise rate is greater than the preset upper limit of temperature rise threshold, the current physiotherapy device is determined to be in a dangerous stimulation state.

6. The method for controlling pulses in a physiotherapy device as described in claim 2, characterized in that, The step of obtaining electrode current compensation and heating power compensation for the patch based on the operating state category specifically includes: When the working state category is understimulation state, the electrode current compensation for the patch increase current is calculated based on the root mean square value of the current electromyography signal and the target electromyography signal; the heating power compensation of the patch is calculated based on the preset heating coefficient. When the operating state category is ideal stimulation state, the current electrode current and heating power remain unchanged; When the working state category is a critical stimulation state, the electrode current compensation for reducing the current of the patch is calculated based on the root mean square value of the current electromyography signal and the target electromyography signal; the heating power compensation of the patch is calculated based on the preset cooling coefficient. When the operating state category is a dangerous stimulus state, the electrode current output and heating of the patch are stopped.

7. The method for controlling pulses in a physiotherapy device as described in claim 6, characterized in that, The control of the patch adjustment current pulse and temperature based on the electrode current compensation and heating power compensation specifically includes: Based on the electrode current compensation and heating power compensation, the target current pulse and target heating power are calculated respectively. Based on the target current pulse and target heating power, the current output and heating power of the patch are controlled to adjust the current pulse and temperature of the patch.

8. The method for controlling pulses in a physiotherapy device as described in claim 6, characterized in that, After maintaining the current electrode current and heating power unchanged, the method further includes: Record the adaptation time from when the patch starts working to when the impedance change rate is less than a preset change value; The fitness score is calculated based on the impedance change rate and the adaptation time. When the fitness score is greater than the preset evaluation value, the current electrode current and heating power remain unchanged. When the fitness score is not greater than the preset evaluation value, the target electromyographic signal and the preset heating coefficient are adjusted based on the preset compensation coefficient, and the electrode current compensation and heating power compensation are recalculated based on the adjusted target electromyographic signal and the preset heating coefficient.

9. A method for controlling pulses in a physiotherapy device as described in any one of claims 1-8, characterized in that, The electromyographic data also includes: the median frequency of the electromyographic signal; prior to controlling the patch to adjust the current pulse and temperature, it also includes: When the median frequency of the electromyographic signal exceeds a preset frequency threshold, the pulse width of the current pulse adjusted by the patch is controlled based on a preset frequency reduction amplitude.

10. A method for controlling pulses in a physiotherapy device as described in any one of claims 1-8, characterized in that, After controlling the patch regulating current pulse and temperature, the method further includes: Record the current current pulse and heating power, and based on the current current pulse and heating power, update the current pulse and heating power of the corresponding patch stored in the database at the time of initial operation.

11. A method for controlling pulses in a physiotherapy device as described in any one of claims 1-8, characterized in that, After controlling the patch regulating current pulse and temperature, the method further includes: Collect the current and temperature parameters input by the user; An alarm is generated when both the current parameter and the temperature parameter are greater than the corresponding preset safety threshold. When both the current parameter and the temperature parameter are not greater than the corresponding preset safety threshold, a corresponding prompt sound is generated and played based on the comparison of the current parameter and the temperature parameter with the current current pulse and temperature, respectively.

12. The method for controlling pulses in a physiotherapy device as described in claim 11, characterized in that, The current and temperature parameters input by the user are collected, including: The system receives current and temperature parameters input by the user through a display interaction module; or, through a voice acquisition module, it receives the user's voice control data, performs semantic analysis on the voice control data, matches current control commands and temperature control commands based on the semantic analysis results, and determines the current and temperature parameters that the user wants to adjust based on the current control commands and temperature control commands.

13. A control system for a physiotherapy device pulse, characterized in that, include: The main control module and the patch connected to the main control module; The patch includes a conductive hydrogel contact layer and electrodes, heating elements and a sensing array disposed on the conductive hydrogel contact layer; The main control module is electrically connected to the electrodes, heating elements and sensor array, and is used to implement the control method of the physiotherapy device pulse as described in any one of claims 1-12.

14. The control system for a physiotherapy device pulse as described in claim 13, characterized in that, Also includes: Current control module and temperature control module; The main control module is connected to the current control module, and thus connected to the electrode; The current control module is used to receive the electrode current control command generated by the main control module based on electrode current compensation, and to control and adjust the current of the electrode based on the electrode current control command. The main control module is connected to the temperature control module, and thus connected to the heating element. The temperature control module is used to receive the heating control command generated by the main control module based on the heating power compensation, and to control and adjust the heating power of the heating element based on the heating control command, so as to control the temperature of the patch.

15. The control system for a physiotherapy device pulse as described in claim 13, characterized in that, It also includes: a voice acquisition module and a display interaction module; both the voice acquisition module and the display interaction module are connected to the main control module; The voice acquisition module is used to receive the user's voice data; The display interaction module is used to receive data input by the user; the user input data includes: current parameters, temperature parameters, and operating mode.

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