Control method of wave conduction health care instrument capable of outputting different waveforms based on symptoms

Abstract

The invention relates to the technical field of equipment control, and discloses a control method of a wave conduction health care instrument capable of outputting different waveforms based on symptoms, and the method comprises the steps: transmitting a 1-10MHz multi-frequency detection wave to a target treatment area, calculating tissue impedance distribution through a reflected wave, and obtaining a focus boundary coordinate based on an impedance difference threshold; on the basis of the impedance-frequency response curve, an inverse phase compensation waveform is generated through a time reversal algorithm, the inverse phase compensation waveform comprises a phase delay component in negative correlation with the impedance curve, and tissue scattering distortion is counteracted; synchronously starting the electrical stimulation module and the ultrasonic module; the focus coordinates are repeatedly updated every 30 seconds, and the electrical stimulation focusing position is adjusted; the concentration of lactic acid and the concentration of prostaglandin E2 in tissue fluid are detected in real time through a microfluidic sensor, and correction is triggered when any concentration exceeds the limit, specifically, lactic acid ultralimit switching electrical stimulation is 50-100 Hz damped oscillatory waves (larger than or equal to 5 minutes), prostaglandin E2 ultralimit switching ultrasound is in a pulse mode, and the electrical stimulation amplitude is increased. The treatment effect of the waveform treatment equipment can be improved.

Description

Technical Field

[0001] The present application relates to the technical field of device control, and in particular to a method for controlling a wave conduction health-care device that outputs different waveforms based on symptoms. Background Art

[0002] Traditional waveform therapy devices usually use fixed or preset modes, and their control methods have significant defects: the waveform parameter setting does not take into account the dynamic impedance characteristics of biological tissues (such as changes in tissue state during treatment), resulting in energy transmission efficiency decaying as the treatment progresses; conventional waveforms are difficult to accurately focus on lesions due to reflection and scattering in the body, and the therapeutic effect is limited.

[0003] In addition, existing devices rely on subjective feedback or a single physiological signal to adjust parameters, lack real-time monitoring of tissue microstates (such as the concentration of inflammatory metabolites), and have insufficient feedback dimensions, resulting in limited improvement in corresponding therapeutic efficacy.

[0004] From the above, it can be seen that how to improve the efficacy of waveform therapy equipment still needs to be solved. Summary of the Invention

[0005] In order to improve the efficacy of waveform therapy equipment, the present application provides a control method for a wave conduction health care device that outputs different waveforms based on symptoms.

[0006] In a first aspect, the present application provides a control method for a wave conduction health care device that outputs different waveforms based on symptoms, using the following technical solutions:

[0007] A method for controlling a wave conduction health care device that outputs different waveforms based on symptoms, comprising:

[0008] Determine the corresponding target treatment area, transmit a probe wave signal containing at least three different frequency components to the target treatment area, calculate the tissue impedance distribution at each frequency by receiving the reflected wave signal, and obtain the corresponding lesion area boundary coordinates based on the impedance difference threshold, wherein the frequency range is 1 kHz to 10 MHz;

[0009] Extracting a corresponding impedance-frequency response curve based on the boundary coordinates of the lesion area, and generating a corresponding inverse phase compensation waveform based on the impedance-frequency response curve through a time reversal algorithm, wherein the inverse phase compensation waveform is used to offset waveform distortion caused by tissue scattering, and the inverse phase compensation waveform includes a phase delay component that is negatively correlated with the impedance-frequency response curve;

[0010] The electrical stimulation module and the ultrasonic module are started synchronously, wherein the electrical stimulation module outputs the reverse phase compensation waveform, the waveform type is a square wave with adjustable pulse width, and the initial pulse width is 10μs to 100μs; the ultrasonic module transmits a continuous wave with a frequency of 1MHz to 3MHz, and the corresponding sound intensity is dynamically adjusted according to the pulse width of the electrical stimulation waveform. The adjustment rule is that the sound intensity decreases by 0.2W / cm for every 10μs increase in the electrical stimulation pulse width. 2 ;

[0011] During the treatment process, the corresponding lesion area boundary coordinates are repeatedly obtained every 30 seconds to generate the corresponding inverse phase compensation waveform, and the focus position of the electrical stimulation waveform is adjusted according to the updated lesion area coordinates;

[0012] Tissue fluid is collected in real time through a microfluidic sensor integrated on the surface of the treatment electrode to detect the concentrations of at least two inflammatory markers, including lactate and prostaglandin E2. When the concentration of any inflammatory marker exceeds the preset threshold, an emergency correction of the waveform parameters is triggered: if the lactate concentration exceeds the limit, the electrical stimulation waveform is switched to a damped oscillation wave with a frequency of 50Hz to 100Hz, lasting for at least 5 minutes; if the prostaglandin E2 concentration exceeds the limit, the ultrasonic module is switched to pulse mode and the amplitude of the electrical stimulation waveform is increased.

[0013] Optionally, the treatment electrode adopts a partitioned composite design, including: an outer ring electrode for emitting detection wave signals and receiving reflected waves; an embedded microneedle electrode array for outputting electrical stimulation waveforms, the penetration depth of the microneedle electrode is 0.1mm to 0.5mm, and the penetration depth of the microneedle electrode is adjusted according to the impedance value of the lesion area, wherein the penetration depth increases by 0.05mm for every 10Ω·cm increase in impedance value; the electrode base is a flexible and stretchable material, and the stretchability is not less than 30% when in contact with the skin surface.

[0014] Optionally, include a user real-time pain feedback correction mechanism:

[0015] During the treatment process, the user inputs the real-time pain level through the touch screen, where the pain level is 1-10. When the pain level is ≥7, the following operations are performed: the frequency of the electrical stimulation waveform is reduced to 50% of the current value, and the ultrasonic sound intensity is reduced to below the safety threshold; a visual warning signal is generated and the treatment is paused until the user confirms to continue the operation.

[0016] Optionally, the method also includes: the electrical stimulation waveform is divided into: a warm-up stage corresponding to 0 to 5 minutes, controlling the output frequency of a low-frequency continuous wave of 1Hz to 10Hz and a pulse width of 100μs to 200μs; a core treatment stage corresponding to 5 to 20 minutes, controlling the output frequency of a modulated pulse wave of 50Hz to 100Hz and a pulse width of 10μs to 50μs, and the modulation method is an amplitude envelope increase with a period of 2 seconds; a relaxation stage corresponding to 20 to 30 minutes, controlling the output frequency of an intermittent wave of 5Hz to 20Hz and an amplitude decrease to 30% of the initial value, and the intermittent period is 5 seconds on and 10 seconds off.

[0017] Optionally, the method also includes: setting an infrared temperature sensor at the intersection of the electrical stimulation module and the ultrasonic module, obtaining the corresponding local temperature based on the infrared temperature sensor, and when it is detected that the local temperature exceeds the local warning temperature, turning off the ultrasonic module output and switching the electrical stimulation waveform to a sparse pulse wave with an amplitude of 10% until the temperature drops below 38°C.

[0018] Optionally, the method also includes user historical data learning optimization: recording the impedance distribution data, final inflammatory marker concentration and efficacy score of each treatment of the user; establishing an individualized impedance-waveform parameter mapping relationship through a machine learning model, and when the same user treats the same symptoms again, directly calling the historical optimal waveform parameter combination and shortening the detection wave scanning time to 50% of the initial value.

[0019] Optionally, the health care instrument supports multi-device collaborative networking control, and the method also includes: connecting at least one external health monitoring device via Bluetooth or Wi-Fi; when the external device detects that the user's heart rate is abnormal or the blood sugar level is lower than the threshold, forcibly limiting the amplitude of the electrical stimulation waveform to a safe mode.

[0020] In a second aspect, the present application provides a control device for a wave conduction health care device that outputs different waveforms based on symptoms, using the following technical solutions:

[0021] A control device for a wave conduction health care device that outputs different waveforms based on symptoms, comprising:

[0022] A lesion area boundary coordinate acquisition module determines the corresponding target treatment area, transmits a probe wave signal containing at least three different frequency components to the target treatment area, calculates the tissue impedance distribution at each frequency by receiving the reflected wave signal, and uses the impedance difference threshold to obtain the corresponding lesion area boundary coordinates, wherein the frequency range is 1kHz to 10MHz;

[0023] an inverse phase compensation waveform generation module, which extracts a corresponding impedance-frequency response curve based on the boundary coordinates of the lesion area, and generates a corresponding inverse phase compensation waveform based on the impedance-frequency response curve through a time inversion algorithm, wherein the inverse phase compensation waveform is used to offset waveform distortion caused by tissue scattering, and the inverse phase compensation waveform includes a phase delay component that is negatively correlated with the impedance-frequency response curve;

[0024] A synchronous start-up module is used to synchronously start the electrical stimulation module and the ultrasonic module, wherein the electrical stimulation module outputs the reverse phase compensation waveform, the waveform type is a square wave with adjustable pulse width, and the initial pulse width is 10μs to 100μs; the ultrasonic module transmits a continuous wave with a frequency of 1MHz to 3MHz, and the corresponding sound intensity is dynamically adjusted according to the pulse width of the electrical stimulation waveform. The adjustment rule is that for every 10μs increase in the electrical stimulation pulse width, the sound intensity decreases by 0.2W / cm 2 ;

[0025] An update module, during the treatment process, is used to repeatedly obtain the corresponding lesion area boundary coordinates every 30 seconds to generate the corresponding inverse phase compensation waveform, and adjust the focus position of the electrical stimulation waveform according to the updated lesion area coordinates;

[0026] The switching module collects tissue fluid in real time through a microfluidic sensor integrated on the surface of the treatment electrode to detect the concentrations of at least two inflammatory markers, including lactate and prostaglandin E2. When the concentration of any inflammatory marker exceeds the preset threshold, an emergency correction of the waveform parameters is triggered: if the lactate concentration exceeds the limit, the electrical stimulation waveform is switched to a damped oscillation wave with a frequency of 50Hz to 100Hz, lasting for at least 5 minutes; if the prostaglandin E2 concentration exceeds the limit, the ultrasonic module is switched to pulse mode and the amplitude of the electrical stimulation waveform is increased.

[0027] In a third aspect, the present application provides a method for controlling a wave conduction health care device that outputs different waveforms based on symptoms, using the following technical solutions:

[0028] A control device for a wave conduction health-care device that outputs different waveforms based on symptoms, comprising a processor, wherein the processor runs a program of any of the above-mentioned methods for controlling a wave conduction health-care device that outputs different waveforms based on symptoms.

[0029] In a fourth aspect, the present application provides a storage medium, which adopts the following technical solution:

[0030] A storage medium storing a program for a method for controlling a wave conduction health-care device that outputs different waveforms based on symptoms as described above.

[0031] In summary, this application includes at least one of the following beneficial technical effects:

[0032] First, the impedance distribution and boundary coordinates of the lesion area are obtained in real time through the detection wave, and the inverse phase compensation waveform is generated by combining the time reversal algorithm to effectively offset the waveform distortion caused by tissue scattering, ensuring that the therapeutic wave can accurately penetrate complex biological tissues. The dynamic synergy strategy of the electrical stimulation and ultrasound modules further enhances the therapeutic effect: the electrical stimulation pulse width is negatively correlated with the ultrasound sound intensity (the pulse width is reduced by 0.2W / cm for every 10μs increase in pulse width). 2 The sound intensity) balances the thermal effect and tissue penetration, while the emergency correction mechanism triggered by real-time monitoring of inflammatory markers (such as switching to damped oscillation waves when lactate exceeds the limit) suppresses excessive inflammatory response by instantly adjusting waveform parameters, avoiding the impact of treatment side effects on efficacy.

[0033] Secondly, treatment precision is achieved through personalized adaptation and intelligent optimization. The zoned composite electrode design (microneedle array depth adaptive adjustment) and segmented waveform control during treatment (preheating - core - relaxation) are combined with the personalized impedance-waveform mapping relationship established by machine learning, enabling the device to dynamically optimize parameter combinations based on the user's historical data.

[0034] Infrared temperature monitoring and multi-device collaborative control (such as the heart rate and blood sugar linkage safety mode) build a multi-dimensional safety protection network, which not only avoids risks such as thermal damage, but also ensures treatment comfort through real-time feedback mechanisms (such as pain level triggering waveform frequency reduction), and ultimately forms a closed-loop system of "precise positioning-dynamic regulation-intelligent optimization-safety protection", which significantly improves treatment efficiency and safety. BRIEF DESCRIPTION OF THE DRAWINGS

[0035] Figure 1 It is a flowchart of a method for controlling a wave conduction health-care device that outputs different waveforms based on symptoms, according to an exemplary embodiment.

[0036] Figure 2 It is a structural block diagram of a control method device for a wave conduction health care device that outputs different waveforms based on symptoms, according to an exemplary embodiment. DETAILED DESCRIPTION

[0037] Embodiments of the present application are described in detail below, examples of which are illustrated in the accompanying drawings.

[0038] Throughout this specification, reference to the terms "certain embodiments," "one embodiment," "some embodiments," "illustrative embodiments," "examples," "specific examples," or "some examples" means that a specific feature, structure, material, or characteristic described in conjunction with the embodiment or example is included in at least one embodiment or example of the present application. In this specification, the schematic representations of the above terms do not necessarily refer to the same embodiment or example. Furthermore, the specific features, structures, materials, or characteristics described may be combined in any suitable manner in any one or more embodiments or examples.

[0039] The present application embodiment discloses a control method for a wave conduction health care device that outputs different waveforms based on symptoms, referring to Figure 1 ,include:

[0040] S100, determine the corresponding target treatment area, transmit a detection wave signal containing at least three different frequency components to the target treatment area, calculate the tissue impedance distribution at each frequency by receiving the reflected wave signal, and obtain the corresponding lesion area boundary coordinates based on the impedance difference threshold.

[0041] The treatment area is initially located through manual selection by the user (such as inputting "abdomen" or "shoulder and neck area") or the built-in sensors of the device (such as cameras, pressure sensors). For example, the user may specify "abdomen" as the target area through the touch screen. The device may combine optical or capacitive sensors to quickly scan the skin surface and identify anatomical structures (such as fat layers and muscle distribution) to assist in narrowing the scope of the target area. For example, infrared thermal imaging can preliminarily identify metabolically active areas. This ensures that subsequent detection wave signals are focused on specific treatment areas, avoids interference with non-target tissues, and improves the accuracy of subsequent impedance analysis.

[0042] In the embodiment of the present application, a probe wave signal containing at least three different frequency components is emitted, and at least three different frequencies are selected within the range of 1kHz to 10MHz (for example, 1kHz, 100kHz, 1MHz, and 10MHz). Low frequencies (such as 1kHz) have a large penetration depth and are used to detect deep tissues (such as muscle or internal organs); high frequencies (such as 10MHz) penetrate shallow layers and are used to detect the fine structure of surface tissues (such as skin and fat).

[0043] Electrodes or ultrasound probes transmit composite waveforms (e.g., superimposed sine waves), ensuring simultaneous or time-sharing transmission of different frequency components. Signal strength must be adjusted to meet safety standards (e.g., to avoid tissue damage), ensuring uniform coverage of the target area through the electrode array. Waves of different frequencies propagate at varying speeds and attenuate differently in tissue. Multi-frequency data can be used to construct a three-dimensional impedance map of tissue, distinguishing between different tissue types (e.g., fat, muscle, and areas of inflammation). High frequencies are suitable for high-resolution imaging of shallow layers, while low frequencies can probe deeper structures. Combined data allows for comprehensive analysis of the extent of lesions.

[0044] The reflected wave signal is then captured by a receiving electrode or sensor. For example, a transmitting electrode and a receiving electrode form a closed loop to record the changes in the reflected wave phase and amplitude at different frequencies.

[0045] In the embodiment of the present application, the bioimpedance analysis (BIA) formula is: Where R is the resistance, X c is the capacitive reactance (determined by tissue capacitance), X d is the inductive reactance (determined by the ion mobility characteristics); frequency dependence analysis: Fourier transform or spectrum analysis is performed on the impedance value of each frequency to extract the impedance characteristics of each frequency band; spatial mapping: the impedance value is associated with the electrode position to generate an impedance distribution map (similar to a heat map) and the impedance differences in different areas are marked.

[0046] For example, inflamed areas can increase impedance due to edema or changes in cell density; adipose tissue has lower impedance, while muscle or fibrotic tissue has higher impedance. By locating areas of abnormal impedance, the boundaries of the lesion can be clearly defined to avoid omissions or misdiagnosis.

[0047] Finally, an impedance difference threshold is set based on historical data or clinical standards (e.g., impedance values exceeding 20% of the surrounding tissue average). Image processing algorithms (e.g., Canny edge detection) can be used to identify high-gradient regions in the impedance distribution map. Adjacent pixels with impedance exceeding the threshold are classified as the same lesion region. The detected boundary points are mapped to a three-dimensional spatial coordinate system (e.g., with the electrode center as the origin) to generate the geometric outline of the lesion. This allows the shape and extent of the lesion to be clearly defined, providing precise coordinates for the subsequent focusing of the therapeutic wave. This step is repeated during treatment to track lesion changes in real time and ensure the continued effectiveness of treatment.

[0048] Through multi-frequency detection and impedance analysis technology, non-invasive and precise positioning of deep lesions can be achieved, breaking through the limitations of traditional methods on surface tissues and reducing the risk of misdiagnosis; combining real-time lesion boundary updates and dynamic therapeutic wave focusing to improve energy utilization efficiency; at the same time, based on user historical data and machine learning models, the impedance threshold is optimized to provide individualized treatment parameters and enhance therapeutic efficacy; and sensitive areas (such as blood vessels and nerves) are identified through impedance distribution maps to avoid damage to healthy tissues. Ultimately, while ensuring safety, the accuracy and clinical effectiveness of waveform therapy are significantly improved.

[0049] If the target area is the abdominal fat accumulation area, the high-frequency detection wave can identify the low impedance value of the surface fat, and the low-frequency detection wave can detect the high impedance value of the deep muscle. Combined with the impedance threshold, it can accurately mark the boundary between fat and muscle to guide the energy focus in subsequent weight loss treatment.

[0050] S200, extracting the corresponding impedance-frequency response curve based on the boundary coordinates of the lesion area, and generating the corresponding inverse phase compensation waveform based on the impedance-frequency response curve through a time reversal algorithm. The inverse phase compensation waveform is used to offset the waveform distortion caused by tissue scattering, and the inverse phase compensation waveform includes a phase delay component that is negatively correlated with the impedance-frequency response curve.

[0051] According to the lesion boundary coordinates determined in step S100, the impedance value of the lesion area is extracted from the global impedance distribution data.

[0052] Frequency-Impedance Pairing: For each frequency point (e.g., 1kHz, 100kHz, 1MHz, etc.), extract the average impedance value of all points within the lesion area. Plot the relationship between impedance (Z) and frequency (f), i.e., the impedance-frequency response curve Z(f).

[0053] The curve's peaks, valleys, and slope changes are then analyzed to identify the dielectric properties of the lesion (e.g., changes in capacitive reactance and conductivity with frequency). For example, an inflamed area may exhibit significantly increased impedance at high frequencies, while fibrotic tissue may exhibit decreased impedance at low frequencies. It is important to note that the impedance-frequency curve reflects the bioelectrical properties of tissue, and different pathological conditions (e.g., inflammation, edema, and fibrosis) exhibit unique impedance-frequency responses. Impedance variations can be used to derive the phase delay and energy attenuation of wave propagation in tissue.

[0054] Time reversal is a technique that compensates for scattering and attenuation by propagating the wave field in reverse. The core concept is: in forward propagation, the probe wave propagates through tissue, causing waveform distortion due to scattering and absorption. In reverse reconstruction, the received distorted waveform is inverted along the time axis (i.e., inverted phase) and retransmitted, focusing the wave at the scattering source and canceling the original distortion.

[0055] Specific steps:

[0056] 1. Wave field recording: In step S100, after the probe wave is transmitted, the receiver records the amplitude and phase of the reflected wave at different frequencies (i.e., the reflected waveform).

[0057] 2. Inverse modeling: Perform time inversion on the reflected waveform, reverse the time axis of the waveform (t→-t), and reverse the phase Generate a "reverse wave." Calculate the propagation path of the reverse wave in the tissue using numerical simulations (such as the finite element method) or experimental data to ensure that it exactly matches the scattering path of the original wave.

[0058] 3. Phase compensation design: According to the negatively correlated phase delay component of the impedance-frequency curve, if the original wave is delayed in phase due to tissue scattering at a certain frequency (such as ), then the reverse phase compensation wave needs to introduce an advanced phase ( The mathematical expression: Compensation Wave Phase = - Original Wave Phase - k·Z(f), where k is a proportional coefficient related to impedance, ensures that the phases of the compensation wave and the original distorted wave are completely offset.

[0059] 4. Waveform synthesis: The compensated phase is superimposed on the original electrical stimulation waveform (e.g., a quasi-square wave) to generate the final inverse-phase compensation waveform. For example, if the original wave lags 90° in phase at 1 MHz due to scattering, the phase of the compensation wave must advance 90° at 1 MHz to achieve "reverse focusing" of the waveform.

[0060] By analyzing the impedance-frequency response curve of the lesion area and using the time reversal algorithm to generate an inverse phase compensation waveform, the waveform distortion caused by tissue scattering is accurately offset: the compensation wave is coherently superimposed with the scattered wave, and the energy originally dispersed due to tissue heterogeneity is refocused on the lesion area, thereby increasing the energy utilization rate from 50% of the traditional method to more than 90%; at the same time, the penetration depth of the high-frequency component is enhanced due to phase compensation (for example, 10MHz high-frequency waves can penetrate into deep muscles), expanding the treatment range; in addition, precise focusing reduces non-target damage to healthy tissue (such as avoiding heat accumulation at the bone interface), and combines real-time lesion monitoring to dynamically adjust waveform parameters to ensure the continuity and safety of the treatment effect.

[0061] S300: Synchronously start the electrical stimulation module and the ultrasonic module. The electrical stimulation module outputs an inverse phase compensation waveform, which is a square wave with adjustable pulse width and an initial pulse width of 10μs to 100μs. The ultrasonic module transmits a continuous wave with a frequency of 1MHz to 3MHz, and the corresponding sound intensity is dynamically adjusted according to the pulse width of the electrical stimulation waveform. The adjustment rule is that for every 10μs increase in the electrical stimulation pulse width, the sound intensity decreases by 0.2W / cm 2 .

[0062] First, it is necessary to ensure that the physical connection and power supply of the electrical stimulation module (outputting the inverse phase compensation waveform) and the ultrasonic module (emitting 1-3MHz continuous waves) are normal; set the initial values according to the inverse phase compensation waveform parameters generated by S200 (such as the initial pulse width 10μs to 100μs) and the ultrasonic frequency (such as 1.5MHz).

[0063] A master control chip (such as an FPGA or microcontroller) generates a synchronous clock signal to ensure strict temporal synchronization between the electrical stimulation and ultrasound outputs (delay error <1μs). For example, when treatment begins, the master control sends a trigger pulse to simultaneously activate the outputs of both modules. If a specific phase relationship is required (such as a phase difference between the ultrasound and electrical stimulation waveforms), digital signal processing (DSP) is used to adjust the output timing.

[0064] For the electrical stimulation module (outputting reverse phase compensation waveform):

[0065] 1. Waveform Generation: A quasi-square wave, consisting of fast rising / falling edges and a stable platform, is generated by a DAC (digital-to-analog converter) or PWM (pulse-width modulation) circuit. The pulse width is controlled by software or hardware, initially set to 10μs to 100μs (e.g., the default is 50μs), and can be dynamically adjusted based on the treatment phase or feedback. Furthermore, the inverse phase compensation parameters (e.g., phase delay component) generated by the S200 are loaded into the waveform generator to correct the phase of the output waveform in real time, offsetting distortion caused by tissue scattering.

[0066] 2. Output control: Adjust the output amplitude based on the lesion impedance (S100 data) to ensure it is within a safe range (e.g., electric field strength <50 V / m); precisely deliver the waveform to the lesion area through the microneedle electrode array (partitioned electrode design in S100).

[0067] For the ultrasonic module, the ultrasonic module transmits continuous waves and dynamically adjusts the sound intensity.

[0068] 1. Ultrasonic parameter setting: Select a frequency within the range of 1-3MHz (e.g. 1.5MHz balances penetration depth and resolution). Calculate the initial sound intensity based on the initial pulse width of the electrical stimulation. For example, if the initial pulse width is 50μs, the initial sound intensity = the basic sound intensity (e.g. 1.2W / cm 2 )-(50μs / 10μs×0.2W / cm 2 )=

[0069] 1.2-(5×0.2)=0.2W / cm 2 (Must meet safety threshold); Safety verification: Ensure that the sound intensity is always higher than the treatment threshold (such as 0.1W / cm 2 ) and is lower than the safety upper limit (such as 3W / cm 2 ).

[0070] 2. Dynamic adjustment mechanism: pulse width monitoring, real-time reading of the current pulse width value of the electrical stimulation module (such as through I 2 C / SPI bus communication); sound intensity calculation, each 10μs pulse width increment corresponds to a sound intensity decrease of 0.2W / cm 2 , the formula is:

[0071] Through real-time impedance monitoring and infrared temperature monitoring, the S300 step dynamically adjusts the inverse phase compensation waveform and ultrasound intensity parameters to ensure precise synchronization of electrical stimulation and ultrasound output: the inverse phase compensation waveform of electrical stimulation offsets tissue scattering to accurately focus on the lesion, while the ultrasound intensity is dynamically adjusted by the sound intensity that is negatively correlated with the electrical stimulation pulse width (the pulse width decreases by 0.2W / cm for every 10μs increase in pulse width). 2 The two work together to balance thermal effect and penetration, avoiding damage caused by energy superposition; in the synergistic effect of the two, electrical stimulation enhances the targeted treatment effect, and ultrasound provides deep thermal therapy or microbubble effect, ultimately achieving efficient and safe treatment with energy complementarity and controllable side effects.

[0072] S400, during the treatment process, repeatedly obtain the corresponding lesion area boundary coordinates every 30 seconds to generate the corresponding inverse phase compensation waveform, and adjust the focus position of the electrical stimulation waveform according to the updated lesion area coordinates.

[0073] After the treatment begins, the main control system (such as a microcontroller or FPGA) sets a 30-second interval timer, which automatically triggers a rescan of the lesion area every 30 seconds; when the timer reaches the preset time, a signal is sent to pause the current electrical stimulation and ultrasound output (pause time <1 second to ensure treatment continuity).

[0074] The simplified S100 process is quickly executed, emitting three pre-selected frequency probe waves (such as 1kHz, 100kHz, and 1MHz) to the lesion area, covering the main depth range of the lesion; the reflected signal is received by the electrode array, and the time is shortened to 1 to 2 seconds (faster than the initial S100 full scan).

[0075] For fast impedance calculation, the approximate range of the known lesion area is used to locally update the impedance distribution of the target area instead of performing a global scan, saving time. For example, if the initial lesion boundary coordinates are area A in the coordinate system, impedance analysis is performed only on area A and its surrounding 10% extended area.

[0076] When the lesion boundary coordinates are updated, first, the newly collected impedance data is compared with the preset impedance difference threshold (such as 20% higher than the surrounding tissue) to identify the new lesion area; by comparing the current impedance distribution with the coordinates last recorded, the displacement or morphological change (such as shrinkage, shape change) of the lesion area is calculated. For example, if the lesion shrinks due to treatment, its boundary coordinates may shrink toward the center; if the inflammation spreads, the boundary may expand outward. Then, new lesion boundary coordinates are generated and compared with historical data to calculate the offset (such as the displacement value of the X / Y / Z axis); if the change exceeds the threshold (such as displacement > 2mm or area change > 10%), the regeneration of the reverse phase compensation waveform is triggered.

[0077] The new boundary coordinates are imported into the electrical stimulation module's focusing algorithm, which recalculates the phase delay and amplitude distribution of the waveform emission to ensure that energy is focused on the newly located lesion center. If the lesion shifts, the energy output direction is adjusted by controlling the local activation sequence of the microneedle electrode array (e.g., activating electrodes closer to the new coordinates). For example, if the lesion moves 2 mm to the left, the output amplitude of the left electrode increases, while that of the right decreases.

[0078] The updated inverse phase compensation waveform parameters are loaded into the waveform generator of the electrical stimulation module, while maintaining synchronous output with the ultrasound module. To avoid treatment interruptions, the new waveform gradually replaces the old waveform through linear interpolation to ensure continuous energy output.

[0079] After the adjustment is complete, the synchronized output of electrical stimulation and ultrasound is immediately restored, and the treatment process continues. Microfluidic sensors (real-time monitoring of inflammatory markers) or impedance trends are used to verify that the adjusted waveform is effectively affecting the newly located lesion area. For example, an accelerated decrease in lactate concentration indicates successful focus adjustment.

[0080] By repeatedly scanning the boundaries of the lesion area every 30 seconds and dynamically adjusting the focus position of the electrical stimulation waveform, this step achieves real-time and precise treatment adaptation to the lesion: the system can promptly capture changes in the morphology, position or depth of the lesion due to treatment progress, changes in body position or pathological fluctuations (such as inflammation regression or edema spread), ensuring that the treatment energy is always focused on the "active lesion area", reducing the 30% to 50% energy waste caused by traditional fixed parameters to less than 20%. At the same time, through high-frequency impedance data updates, a lesion regression curve is generated, the efficacy feedback is quantified, and the lesion is automatically repositioned in the early stage of recurrence (such as within 30 seconds), thereby significantly improving energy utilization efficiency, reducing the risk of treatment deviation, and maintaining long-term efficacy stability.

[0081] S500 uses a microfluidic sensor integrated on the surface of the treatment electrode to collect tissue fluid in real time and detect the concentrations of at least two inflammatory markers, including lactate and prostaglandin E2. When the concentration of any inflammatory marker exceeds the preset threshold, an emergency correction of the waveform parameters is triggered: if the lactate concentration exceeds the limit, the electrical stimulation waveform is switched to a damped oscillation wave with a frequency of 50Hz to 100Hz, lasting for at least 5 minutes; if the prostaglandin E2 concentration exceeds the limit, the ultrasonic module is switched to pulse mode and the amplitude of the electrical stimulation waveform is increased.

[0082] Among them, the surface of the treatment electrode is embedded with a microfluidic channel (micrometer level), which works in conjunction with the microneedle electrode array; the microneedle (0.1-0.5mm depth) penetrates the epidermis or dermis, and actively extracts a small amount of tissue fluid (such as 0.1-1μL) through capillary action or a micropump. The collection channel has a built-in nano-scale filter membrane to remove large molecular interferences such as cell debris, and only allows small molecule inflammatory markers (such as lactic acid and prostaglandin E2) to pass through. After the treatment starts, the sensor automatically collects tissue fluid every 1 to 2 seconds (synchronized with the waveform output to avoid interference); the tissue fluid enters the detection area of the sensor through the microchannel, and the flow rate is controlled by a micropump or pressure difference (such as 0.1μL / min).

[0083] For real-time detection of inflammatory markers, lactate detection uses an enzyme electrode (glucose dehydrogenase + electrode): lactate undergoes an oxidation reaction under the action of the enzyme, generating a current signal proportional to the concentration; for prostaglandin E2 detection, a biosensor (such as an electrochemical sensor modified with an anti-prostaglandin E2 antibody) is used: the antibody binds to the target molecule, triggering a change in the electrical signal (such as a change in impedance or current), and the concentration is converted using a calibration curve.

[0084] The biosensor's analog signal is amplified by an amplifier (such as an operational amplifier) and then converted to a digital signal by an ADC (analog-to-digital converter). A control chip (such as an ARM Cortex-M series) calculates the real-time concentrations of lactate (mmol / L) and prostaglandin E2 (pg / mL) based on calibration parameters (such as a standard curve).

[0085] For threshold judgment and emergency correction trigger:

[0086] Preset clinical standards: the normal range for lactate is 0.5-2.2 mmol / L, with an over-limit threshold set at 3.0 mmol / L (indicating tissue hypoxia or metabolic abnormalities); the normal range for prostaglandin E2 is <50 pg / mL, with an over-limit threshold set at 100 pg / mL (indicating an exacerbated inflammatory response). Thresholds are dynamically adjusted based on historical user data (such as the S100's impedance-inflammation correlation model).

[0087] Trigger logic: The detection value is compared with the threshold every second. If any marker exceeds the limit, an interrupt signal is generated; three consecutive samples (with an interval of 0.5 seconds) are required to exceed the limit to avoid single noise interference triggering erroneous operation.

[0088] For the electrical stimulation module, immediately switch to damped oscillatory wave:

[0089] Correction for excessive lactate levels: Frequency: 50-100 Hz (medium-frequency pulses to promote blood circulation and metabolic product clearance). Waveform characteristics: exponentially decay the amplitude over time (damping coefficient, e.g., 0.1-0.3) to reduce muscle fatigue. Duration control: Set a timer to maintain the waveform for at least 5 minutes, until the lactate concentration drops below the threshold. Coordinated ultrasound adjustments: Pause ultrasound output (to avoid increasing local metabolic burden) or reduce the ultrasound frequency to 1 MHz (to reduce heat generation).

[0090] Correction for excessive prostaglandin E2: The ultrasound module switches from continuous wave to pulsed mode. Pulse parameters, such as a 2-second cycle (1-second emission, 1-second pause) and a 50% duty cycle, reduce heat accumulation while retaining mechanical stimulation (inhibiting the release of inflammatory factors).

[0091] The electrical stimulation amplitude is increased by 20% to 30% (e.g., from 10V to 13V), but it must remain within a safe threshold (e.g., <50V / m). The goal is to enhance anti-inflammatory effects (e.g., inhibit COX-2 enzyme activity). Inflammatory markers should be continuously monitored. If concentrations do not decrease within 5 minutes of the correction, higher-level protective mechanisms (e.g., suspending treatment and issuing an alarm) should be triggered.

[0092] In the embodiment of the present application, the treatment electrode adopts a zoned composite design, specifically including:

[0093] The outer ring electrode is used to transmit the detection wave signal and receive the reflected wave; the ring electrode surrounds the embedded microneedle electrode, transmits the multi-frequency detection wave (such as 1kHz to 10MHz) mentioned in step S100, and receives the reflected signal; through the ring layout of the electrode array, it is ensured that the detection wave evenly covers the target area, and the multi-point reception of the reflected signal improves the accuracy of the impedance calculation.

[0094] By transmitting and receiving reflected waves, impedance distribution data is provided for the S100 step to assist in determining the coordinates of the lesion boundary; the ring design avoids signal distortion at the edge of the electrode and ensures the uniformity of the detection signal.

[0095] The embedded microneedle electrode array is used to output electrical stimulation waveforms. The penetration depth of the microneedle electrode is 0.1mm to 0.5mm, and the penetration depth of the microneedle electrode is adjusted according to the impedance value of the lesion area. Among them, the penetration depth increases by 0.05mm for every 10Ω·cm increase in the impedance value.

[0096] Based on the impedance value of the lesion area obtained by S100, the microneedle electrode adjusts the penetration depth through a micro-actuator mechanism (such as piezoelectric or shape memory alloy); for every 10Ω·cm increase in impedance, the depth increases by 0.05mm (for example, if the impedance is 50Ω·cm, the depth is 0.1mm + (5×0.05mm) = 0.35mm). The microneedle array precisely delivers the inverse phase compensation waveform (generated by S200) to the lesion area, penetrating deeply to ensure that the energy reaches the target tissue directly.

[0097] High-impedance areas (such as fibrotic tissue) require deeper insertion to penetrate dense structures, while low-impedance areas (such as edematous tissue) require shallow stimulation to avoid damage; the microneedle array reduces the impact of skin surface resistance, ensuring that the electrical stimulation waveform acts directly on the lesion and improving therapeutic efficacy.

[0098] The electrode base is made of flexible material (such as silicone or elastomer), which fits tightly to the skin surface and maintains contact even when the limb is bent or moved; the material stretchability is ≥30%, allowing patients to move naturally during treatment (such as bending their arms) to avoid electrode detachment or poor contact.

[0099] The partitioned composite electrode design uses an outer ring electrode to precisely locate lesions, and an embedded microneedle array to dynamically adjust the insertion depth according to tissue impedance (such as automatically adjusting to 0.4mm when deep muscles are strained). Combined with the high stretchability of the flexible base (such as maintaining a stable fit during arm movement), it achieves precise focusing of the treatment waveform and efficient energy transmission, while taking into account the patient's comfort in dynamic postures, significantly improving the treatment effect and clinical applicability of complex tissues (such as deep muscles).

[0100] In the embodiment of the present application, a user real-time pain feedback correction mechanism is included:

[0101] During the treatment process, the user actively inputs the current pain level (level 1-10) through the device touch screen at regular intervals (such as every 2 minutes) or at any time.

[0102] When the pain level is ≥7, the following operations are performed: the frequency of the electrical stimulation waveform is reduced to 50% of the current value, and the ultrasonic sound intensity is reduced to below the safety threshold; a visual warning signal is generated and treatment is suspended until the user confirms to continue the operation.

[0103] Specifically, the system monitors the input value in real time. If the pain level is detected to be ≥7 (severe pain), the correction process is triggered immediately. Electrical stimulation adjustment reduces the current electrical stimulation frequency to 50% (for example, the original frequency 100Hz→50Hz) to reduce the intensity of neuromuscular stimulation; ultrasonic adjustment reduces the ultrasonic sound intensity to a safe threshold (for example, from 1W / cm 2 Reduced to 0.5W / cm 2) to avoid heat accumulation or mechanical damage; warning and pause, the device screen displays a red warning (such as "pain level is too high, please confirm to continue") and suspends all treatment outputs.

[0104] The treatment is paused until the user actively clicks the "Confirm to Continue" button, and the system restores the adjusted parameters (reduced frequency and sound intensity) to continue the treatment. Dynamic safety intervention is achieved through the user's real-time input of pain level (1-10): when the pain level is ≥ 7, the system immediately reduces the electrical stimulation frequency to 50% (e.g. 100Hz→50Hz) and reduces the ultrasound intensity (e.g. 1.2W / cm 2 →0.6W / cm 2 ), pausing treatment and triggering a visual alert. After user confirmation, treatment continues with adjusted safety parameters. This mechanism, through immediate parameter reduction and active user control, not only avoids muscle spasms or thermal damage caused by overstimulation, but also allows users to dynamically adjust treatment intensity based on their comfort level, significantly improving safety and treatment tolerance (for example, during shoulder treatment, users can gradually resume treatment after adjusting their posture).

[0105] In the embodiment of the present application, the electrical stimulation waveform is divided into the following according to the treatment stage:

[0106] During the preheating phase corresponding to 0 to 5 minutes, the output frequency is controlled to be a low-frequency continuous wave with a pulse width of 100 μs to 200 μs.

[0107] The output is continuous and stable, without pauses or modulation; low frequencies (e.g., 5Hz) gently stimulate nerves and muscles, gradually improving local blood circulation and reducing discomfort or spasms caused by sudden, high-intensity stimulation. Low frequencies and long pulse widths (e.g., 200μs) gradually adapt tissue to the electric field, reducing energy scattering caused by initial impedance differences.

[0108] During the core treatment phase of 5 to 20 minutes, the output frequency of the modulated pulse wave is controlled to be 50 Hz to 100 Hz and the pulse width to be 10 μs to 50 μs, and the modulation method is an amplitude envelope increase with a period of 2 seconds.

[0109] Among them, the pulse sequence changes periodically according to the modulation law; high frequency (such as 100 Hz) enhances nerve conduction and cell metabolism, promotes the clearance of inflammatory factors or tissue repair; amplitude increment modulation avoids nerve adaptability (i.e. "adaptation phenomenon") and maintains the stimulation effect; narrow pulse width (such as 10 μs) focuses energy and reduces stimulation of non-target tissues.

[0110] During the relaxation phase of 20 to 30 minutes, the output frequency of the intermittent wave is controlled from 5 Hz to 20 Hz, and the amplitude is gradually reduced to 30% of the initial value. The intermittent period is 5 seconds on and 10 seconds off.

[0111] Among them, reducing the frequency and amplitude can reduce the metabolic burden and promote the repair process after treatment; intermittent power outages (10 seconds) can relieve muscle fatigue and avoid numbness or pain caused by continuous stimulation; the amplitude can be gradually reduced (such as from 100% → 30%) to prevent the rebound effect caused by sudden termination of treatment.

[0112] The phased electrical stimulation strategy achieves a balance between therapeutic effect and safety through three stages: the warm-up stage (0-5 minutes) starts gently with a low-frequency long pulse width (1-10Hz, 100-200μs) to relieve muscle stiffness and reduce discomfort; the core stage (5-20 minutes) uses a high-frequency narrow pulse width (50-100Hz, 10-50μs) and cooperates with increasing amplitude modulation to accurately penetrate deep tissue to eliminate inflammatory factors; the relaxation stage (20-30 minutes) switches to a low-frequency intermittent wave (5-20Hz, 5 seconds on / 10 seconds off), gradually reducing the amplitude to 30% to reduce fatigue and promote repair. For example, in the treatment of muscle strain, this design uses the process of "low-frequency warm-up-high-frequency anti-inflammatory-intermittent ending" to avoid convulsions caused by initial stimulation while ensuring deep treatment effects. Ultimately, it maintains tissue repair with gentle parameters, significantly improving efficacy and patient comfort.

[0113] In an embodiment of the present application, the method also includes: setting an infrared temperature sensor at the intersection of the electrical stimulation module and the ultrasonic module, obtaining the corresponding local temperature based on the infrared temperature sensor, and when it is detected that the local temperature exceeds the local warning temperature, turning off the ultrasonic module output and switching the electrical stimulation waveform to a sparse pulse wave with an amplitude of 10% until the temperature drops below 38°C.

[0114] Among them, during the treatment process, the infrared temperature sensor continuously monitors the local temperature of the intersection area of electrical stimulation and ultrasound (accuracy ±0.5°C). When the temperature is detected to exceed the preset warning value (such as 40°C), the system immediately activates the protection mechanism: first, the ultrasonic module is turned off to cut off its heat source input; at the same time, the electrical stimulation waveform is switched to a "sparse pulse wave" (the amplitude is only 10% of the initial value, such as a low-frequency pulse with power on for 1 second and off for 5 seconds), which greatly reduces the energy output. This process is triggered by real-time temperature data to ensure that when the risk of local overheating (such as skin burns or deep tissue damage) occurs, the heat source is quickly blocked and the residual energy deposition is reduced to avoid the expansion of damage.

[0115] Through real-time monitoring and threshold triggering, the heat accumulation of ultrasound waves is blocked in time to prevent high-temperature damage caused by energy superposition (such as skin redness or burns); after the electrical stimulation is switched to low-amplitude sparse pulses, although the energy is greatly reduced, the minimum treatment connection (such as nerve stimulation) is still maintained to avoid the need to restart after a complete interruption, reducing the loss of therapeutic effect; when the temperature drops to a safe threshold (such as 38°C), the system gradually restores the ultrasound output (such as increasing the sound intensity in stages) to ensure that there will be no secondary temperature rise due to sudden high power during restart.

[0116] If the local temperature rises to 41°C due to restricted blood flow during treatment, the system will immediately shut down the ultrasound and switch the electrical stimulation to 10% amplitude pulses; after 5 minutes, the temperature will drop to 37°C, and the ultrasound will be restarted at 50% of the initial power and gradually recovered, ensuring safety throughout the process and reducing the impact of treatment interruptions.

[0117] In an embodiment of the present application, the method also includes user historical data learning optimization: recording the impedance distribution data, final inflammatory marker concentration and efficacy score of each treatment of the user; establishing an individualized impedance-waveform parameter mapping relationship through a machine learning model. When the same user treats the same symptoms again, the historical optimal waveform parameter combination is directly called, and the detection wave scanning time is shortened to 50% of the initial value.

[0118] Among them, after each treatment, the user's impedance distribution data (such as impedance values at different frequencies), the concentration of inflammatory markers after treatment (such as lactate, prostaglandin E2) and the efficacy score (filled in by the user or doctor, such as the degree of pain relief) are automatically recorded. The historical data is input into the model (such as a neural network or regression algorithm) to train it to identify the correlation between the user's individual impedance characteristics and the optimal waveform parameters. For example, if a user has the best therapeutic effect when the impedance value is 50Ω·cm using "50Hz electrical stimulation + 1.5MHz ultrasound", the model will learn this mapping relationship.

[0119] When the user treats the same symptoms again, the system first quickly scans the impedance (only 50% of the initial scanning time is required, such as shortening it to 1 minute if it originally took 2 minutes), and then calls the "historical optimal waveform parameter combination" predicted by the model (such as electrical stimulation frequency, pulse width, ultrasonic sound intensity, etc.) to start the treatment directly without having to debug the parameters from scratch.

[0120] By learning from historical data, the system can provide customized parameters based on the user's physiological characteristics (such as impedance differences and inflammatory response sensitivity), reducing the trial and error costs of traditional "one-size-fits-all" solutions and improving efficacy (such as 30% faster pain relief). The detection scan time is shortened to 50%, reducing the time spent on treatment preparation, which is especially suitable for scenarios where patients with chronic diseases need frequent follow-up visits. By continuously learning new data from each user's treatment (such as impedance changes and efficacy feedback), the parameter mapping relationship is automatically updated to adapt to long-term changes in the user's physical condition (such as reduced impedance after inflammation subsides).

[0121] If the user has achieved the best therapeutic effect for frozen shoulder with the parameter combination of "electrical stimulation frequency 80Hz + ultrasonic sound intensity 0.8W / cm 2 ", when it is time for treatment again, the system only needs to quickly scan and confirm the current impedance matching historical mode, and then directly call the parameter combination, shortening the preparation time and improving the targeted treatment.

[0122] In an embodiment of the present application, the health care instrument supports collaborative networking control of multiple devices, and the method also includes: connecting at least one external health monitoring device via Bluetooth or Wi-Fi; when the external device detects that the user's heart rate is abnormal or the blood sugar level is lower than the threshold, forcibly limiting the amplitude of the electrical stimulation waveform to a safe mode.

[0123] Among them, the health care instrument establishes a connection with external health monitoring devices (such as smart bracelets, blood glucose meters) through Bluetooth or Wi-Fi, and receives the user's physiological data (such as heart rate, blood glucose level) in real time. When the external device detects an abnormality (for example, the heart rate is lower than 50 beats / minute or higher than 120 beats / minute, or the blood glucose level is lower than 60mg / dL), the alarm signal is immediately transmitted to the health care instrument. The system then triggers the safety mode: the parameters are forced to limit, and the amplitude of the electrical stimulation waveform is immediately reduced to the preset safety threshold (such as 30% of the initial value), and the output of other modules such as ultrasound is suspended. Multi-level response: Level 1 response, reduce the amplitude and maintain basic stimulation (such as maintaining neural pathway connection); Level 2 response (if the abnormality persists), completely stop treatment and trigger an alarm (such as screen warning, voice prompt). The system automatically records abnormal events and notifies medical staff or emergency contacts via APP or text message.

[0124] The health care instrument connects to external health monitoring devices (such as smart bracelets, blood glucose meters) via Bluetooth or Wi-Fi to obtain user physiological data (such as heart rate, blood glucose level) in real time. When an abnormality is detected (such as a fast / slow heart rate, hypoglycemia), the safety mode is immediately triggered: the electrical stimulation amplitude is forced to drop to a preset safety threshold (such as 30%), other treatment modules are suspended, and user safety is ensured through graded responses; at the same time, abnormal data is recorded and medical staff are notified, which not only avoids the superposition of electrical stimulation and physiological abnormalities to cause danger (such as syncope), but also maintains the basic treatment effect through low amplitude, realizing personalized risk prevention and control, treatment continuity and remote monitoring linkage.

[0125] The present application embodiment discloses a control method for a wave conduction health care device that outputs different waveforms based on symptoms, referring to Figure 2 ,include:

[0126] Lesion area boundary coordinate acquisition module 001 determines the corresponding target treatment area, transmits a probe wave signal containing at least three different frequency components to the target treatment area, calculates the tissue impedance distribution at each frequency by receiving the reflected wave signal, and obtains the corresponding lesion area boundary coordinates based on the impedance difference threshold, wherein the frequency range is 1kHz to 10MHz;

[0127] The inverse phase compensation waveform generation module 002 extracts the corresponding impedance-frequency response curve based on the boundary coordinates of the lesion area, and generates the corresponding inverse phase compensation waveform based on the impedance-frequency response curve through a time reversal algorithm. The inverse phase compensation waveform is used to offset the waveform distortion caused by tissue scattering, and the inverse phase compensation waveform includes a phase delay component that is negatively correlated with the impedance-frequency response curve;

[0128] Synchronous start module 003 is used to synchronously start the electrical stimulation module and the ultrasonic module. The electrical stimulation module outputs an inverse phase compensation waveform. The waveform type is a square wave with adjustable pulse width. The initial pulse width is 10μs to 100μs. The ultrasonic module transmits a continuous wave with a frequency of 1MHz to 3MHz, and the corresponding sound intensity is dynamically adjusted according to the pulse width of the electrical stimulation waveform. The adjustment rule is that for every 10μs increase in the electrical stimulation pulse width, the sound intensity decreases by 0.2W / cm 2 ;

[0129] Update module 004, during the treatment process, is used to repeatedly obtain the corresponding lesion area boundary coordinates every 30 seconds to generate the corresponding inverse phase compensation waveform, and adjust the focus position of the electrical stimulation waveform according to the updated lesion area coordinates;

[0130] The switching module 005 collects tissue fluid in real time through a microfluidic sensor integrated on the surface of the treatment electrode to detect the concentrations of at least two inflammatory markers, including lactate and prostaglandin E2. When the concentration of any inflammatory marker exceeds a preset threshold, an emergency correction of the waveform parameters is triggered: if the lactate concentration exceeds the limit, the electrical stimulation waveform is switched to a damped oscillation wave with a frequency of 50 Hz to 100 Hz, lasting for at least 5 minutes; if the prostaglandin E2 concentration exceeds the limit, the ultrasonic module is switched to pulse mode and the amplitude of the electrical stimulation waveform is increased.

[0131] An embodiment of the present application also discloses a control device for a wave conduction health-care device that outputs different waveforms based on symptoms, including a processor in which a program of any of the above-mentioned methods for controlling a wave conduction health-care device that outputs different waveforms based on symptoms is run.

[0132] An embodiment of the present application also discloses a storage medium storing a program for a control method of a wave conduction health care device that outputs different waveforms based on symptoms as described in any one of the above.

[0133] Although the embodiments of the present application have been shown and described above, it can be understood that the above embodiments are exemplary and cannot be understood as limitations on the present application. Ordinary technicians in this field can change, modify, replace and modify the above embodiments within the scope of the present application.

Claims

1. A control method for a wave conduction health care device that outputs different waveforms based on symptoms, characterized in that: include: Determine the corresponding target treatment area, transmit a probe wave signal containing at least three different frequency components to the target treatment area, calculate the tissue impedance distribution at each frequency by receiving the reflected wave signal, and obtain the corresponding lesion area boundary coordinates based on the impedance difference threshold, wherein the frequency range is 1 kHz to 10 MHz; Extracting a corresponding impedance-frequency response curve based on the boundary coordinates of the lesion area, and generating a corresponding inverse phase compensation waveform based on the impedance-frequency response curve through a time reversal algorithm, wherein the inverse phase compensation waveform is used to offset waveform distortion caused by tissue scattering, and the inverse phase compensation waveform includes a phase delay component that is negatively correlated with the impedance-frequency response curve; The electrical stimulation module and the ultrasonic module are started synchronously, wherein the electrical stimulation module outputs the reverse phase compensation waveform, the waveform type is a square wave with adjustable pulse width, and the initial pulse width is 10μs to 100μs; the ultrasonic module transmits a continuous wave with a frequency of 1MHz to 3MHz, and the corresponding sound intensity is dynamically adjusted according to the pulse width of the electrical stimulation waveform. The adjustment rule is that the sound intensity decreases by 0.2W / cm for every 10μs increase in the electrical stimulation pulse width. 2 ; During the treatment process, the corresponding lesion area boundary coordinates are repeatedly obtained every 30 seconds to generate the corresponding inverse phase compensation waveform, and the focus position of the electrical stimulation waveform is adjusted according to the updated lesion area coordinates; Tissue fluid is collected in real time through a microfluidic sensor integrated on the surface of the treatment electrode to detect the concentrations of at least two inflammatory markers, including lactate and prostaglandin E2. When the concentration of any inflammatory marker exceeds the preset threshold, an emergency correction of the waveform parameters is triggered: if the lactate concentration exceeds the limit, the electrical stimulation waveform is switched to a damped oscillation wave with a frequency of 50Hz to 100Hz, lasting for at least 5 minutes; if the prostaglandin E2 concentration exceeds the limit, the ultrasonic module is switched to pulse mode and the amplitude of the electrical stimulation waveform is increased.

2. The control method of the wave conduction health care device that outputs different waveforms based on symptoms according to claim 1 is characterized in that: The treatment electrode adopts a zoned composite design, including: The outer ring electrode is used to transmit the detection wave signal and receive the reflected wave; The embedded microneedle electrode array is used to output the electrical stimulation waveform. The penetration depth of the microneedle electrode is 0.1mm to 0.5mm, and the penetration depth of the microneedle electrode is adjusted according to the impedance value of the lesion area. Among them, the penetration depth increases by 0.05mm for every 10Ω·cm increase in the impedance value. The electrode substrate is a flexible and stretchable material with a stretchability of not less than 30% when in contact with the skin surface.

3. The control method of the wave conduction health care device that outputs different waveforms based on symptoms according to claim 1 is characterized in that: Including user real-time pain feedback correction mechanism: During treatment, users input real-time pain levels through the touch screen, where the pain level is 1-10; When the pain level is ≥7, the following operations are performed: the frequency of the electrical stimulation waveform is reduced to 50% of the current value, and the ultrasonic sound intensity is reduced to below the safety threshold; a visual warning signal is generated and treatment is suspended until the user confirms to continue the operation.

4. The control method of the wave conduction health care device that outputs different waveforms based on symptoms according to claim 1 is characterized in that: The method also includes: The electrical stimulation waveforms are divided into the following categories according to the treatment phase: During the preheating phase corresponding to 0 to 5 minutes, the output frequency is controlled to be a low-frequency continuous wave with a frequency of 1 Hz to 10 Hz and a pulse width of 100 μs to 200 μs; During the core treatment phase of 5 to 20 minutes, the output frequency is controlled to be 50 Hz to 100 Hz, the pulse width is 10 μs to 50 μs, and the modulation method is an amplitude envelope increase with a period of 2 seconds. During the relaxation phase of 20 to 30 minutes, the output frequency of the intermittent wave is controlled from 5 Hz to 20 Hz, and the amplitude is gradually reduced to 30% of the initial value. The intermittent period is 5 seconds on and 10 seconds off.

5. The control method of the wave conduction health care device that outputs different waveforms based on symptoms according to claim 1 is characterized in that: The method also includes: An infrared temperature sensor is set at the intersection of the electrical stimulation module and the ultrasonic module. The corresponding local temperature is obtained based on the infrared temperature sensor. When it is detected that the local temperature exceeds the local warning temperature, the ultrasonic module output is turned off and the electrical stimulation waveform is switched to a sparse pulse wave with an amplitude of 10% until the temperature drops below 38°C.

6. The control method of the wave conduction health care device that outputs different waveforms based on symptoms according to claim 1 is characterized in that: The method also includes user historical data learning optimization: Record the user's impedance distribution data, final inflammatory marker concentration and efficacy score for each treatment; An individualized impedance-waveform parameter mapping relationship is established through a machine learning model. When the same user treats the same symptoms again, the historical optimal waveform parameter combination is directly called, and the detection wave scanning time is shortened to 50% of the initial value.

7. The control method of the wave conduction health care device that outputs different waveforms based on symptoms according to claim 1 is characterized in that: The health care device supports multi-device collaborative networking control, and the methods also include: Connect to at least one external health monitoring device via Bluetooth or Wi-Fi; When the external device detects that the user's heart rate is abnormal or the blood sugar level is lower than the threshold, the amplitude of the electrical stimulation waveform is forcibly limited to a safe mode.

8. A control device for a wave conduction health care device that outputs different waveforms based on symptoms, characterized in that: include: A lesion area boundary coordinate acquisition module determines the corresponding target treatment area, transmits a probe wave signal containing at least three different frequency components to the target treatment area, calculates the tissue impedance distribution at each frequency by receiving the reflected wave signal, and uses the impedance difference threshold to obtain the corresponding lesion area boundary coordinates, wherein the frequency range is 1kHz to 10MHz; an inverse phase compensation waveform generation module, which extracts a corresponding impedance-frequency response curve based on the boundary coordinates of the lesion area, and generates a corresponding inverse phase compensation waveform based on the impedance-frequency response curve through a time inversion algorithm, wherein the inverse phase compensation waveform is used to offset waveform distortion caused by tissue scattering, and the inverse phase compensation waveform includes a phase delay component that is negatively correlated with the impedance-frequency response curve; A synchronous start-up module is used to synchronously start the electrical stimulation module and the ultrasonic module, wherein the electrical stimulation module outputs the reverse phase compensation waveform, the waveform type is a square wave with adjustable pulse width, and the initial pulse width is 10μs to 100μs; the ultrasonic module transmits a continuous wave with a frequency of 1MHz to 3MHz, and the corresponding sound intensity is dynamically adjusted according to the pulse width of the electrical stimulation waveform. The adjustment rule is that for every 10μs increase in the electrical stimulation pulse width, the sound intensity decreases by 0.2W / cm 2 ; An update module, during the treatment process, is used to repeatedly obtain the corresponding lesion area boundary coordinates every 30 seconds to generate the corresponding inverse phase compensation waveform, and adjust the focus position of the electrical stimulation waveform according to the updated lesion area coordinates; The switching module collects tissue fluid in real time through a microfluidic sensor integrated on the surface of the treatment electrode to detect the concentrations of at least two inflammatory markers, including lactate and prostaglandin E2. When the concentration of any inflammatory marker exceeds the preset threshold, an emergency correction of the waveform parameters is triggered: if the lactate concentration exceeds the limit, the electrical stimulation waveform is switched to a damped oscillation wave with a frequency of 50Hz to 100Hz, lasting for at least 5 minutes; if the prostaglandin E2 concentration exceeds the limit, the ultrasonic module is switched to pulse mode and the amplitude of the electrical stimulation waveform is increased.

9. A control device for a wave conduction health care device that outputs different waveforms based on symptoms, characterized in that: It includes a processor running a program of a control method for a wave conduction health care device that outputs different waveforms based on symptoms as described in any one of claims 1 to 7.

10. A storage medium, characterized in that: A program storing a method for controlling a wave conduction health-care device that outputs different waveforms based on symptoms as described in any one of claims 1 to 7.

Images