A local shaping beauty instrument based on bioelectricity and a control method thereof

Abstract

This application provides a bioelectric-based local body sculpting and beauty device and its control method. The method involves: determining the impedance detection sequence of a selected area; extracting the local contraction frequency of the selected area based on the impedance fluctuation curve; determining the symmetrical region of the selected area and extracting the corresponding symmetrical contraction frequency; performing symmetrical frequency analysis based on the local and symmetrical contraction frequencies to determine the contraction frequency over-schedule of the selected area; determining whether the selected area is a contraction over-schedule area based on the contraction frequency over-schedule; and adjusting the output signal frequency of the bioelectrode in the contraction over-schedule area based on the contraction frequency over-schedule. This method can adjust the pulse current signal frequency based on the impedance fluctuations of both sides of the area, avoiding deviations in the perceived effect between the two sides and improving the user's comfort during use of the local body sculpting and beauty device.

Description

Technical Field

[0001] This application relates to the field of signal frequency control technology, and more specifically, to a bioelectric-based local shaping and beauty device and its control method. Background Technology

[0002] Localized body sculpting and beauty devices are beauty therapy devices based on biomimetic current stimulation technology. At their core, they output modulated weak currents to local tissues on the skin surface, simulating bio-pulse currents of nerve signals, causing rhythmic contractions of the target muscle groups, thereby improving the metabolic state and blood circulation of local tissues.

[0003] In existing technologies, due to differences in users' physiological characteristics, stimulation with bio-pulse currents with the same control parameters can lead to different sensations. Even on the same user, symmetrical tissue areas can easily produce different muscle contractions due to differences in muscle density, fat thickness, or skin resistance. This results in inconsistent sensations on both sides of the body when using a local shaping beauty device with multiple current outputs, thus reducing the user experience of the local shaping beauty device. Summary of the Invention

[0004] This application provides a local shaping beauty device based on bioelectricity and its control method, which can adjust the frequency of pulse current signal based on the impedance fluctuation of both sides, avoid the deviation of the body feeling effect in both sides, and improve the comfort of users of the local shaping beauty device.

[0005] In a first aspect, this application provides a control method for a local shaping and beauty device based on bioelectricity. This method can be executed by a network device, or it can be executed by a chip configured in the network device. This application does not limit the method in this regard.

[0006] Specifically, the method includes:

[0007] The bioelectrode in the selected area is subjected to superimposed detection pulse signals, and impedance analysis is performed based on the pulse feedback signal of the detection pulse signals to determine the impedance detection sequence of the selected area.

[0008] An impedance fluctuation curve is constructed based on the impedance detection sequence to obtain the bioelectric signal of the selected region. Coupling characteristics are analyzed based on the bioelectric signal of the selected region and the impedance fluctuation curve to obtain the signal coupling index.

[0009] When the signal linkage characteristic is higher than a preset threshold, the local contraction frequency of the selected area is extracted based on the impedance fluctuation curve.

[0010] Determine the symmetrical region of the selected area, extract the symmetrical contraction frequency corresponding to the symmetrical region, and perform over-schedule comparison between the local contraction frequency and the symmetrical contraction frequency to determine the over-schedule of the contraction frequency corresponding to the selected area.

[0011] Based on the contraction frequency overschedule, it is determined whether the selected region is a contraction overschedule region, and the contraction frequency overschedule is used as a control parameter to adjust the output signal frequency of the bioelectrode in the contraction overschedule region.

[0012] In conjunction with the first aspect, in certain implementations of the first aspect, determining the impedance detection sequence of the selected region by performing impedance analysis based on the pulse feedback signal of the detection pulse signal specifically includes:

[0013] Obtain the instantaneous current response corresponding to each time point in the pulse feedback signal;

[0014] The pulse feedback signal and the detection pulse signal are time-aligned, and the detection impedance is determined based on the instantaneous current response and the voltage amplitude of the detection pulse signal.

[0015] An impedance detection sequence is generated based on the detection impedance at each time point.

[0016] In conjunction with the first aspect, in certain implementations of the first aspect, coupling characteristic analysis is performed based on the bioelectrical signal of the selected region and the impedance fluctuation curve to obtain signal coupling indices, specifically including:

[0017] Extract the signal period from the impedance fluctuation curve;

[0018] Multiple delay times are generated based on the signal period of the impedance fluctuation curve. For any delay, a cross-correlation function is used to calculate the cross-correlation value, and the maximum value of the cross-correlation function is used as the signal coupling index.

[0019] In conjunction with the first aspect, in some implementations of the first aspect, extracting the local contraction frequency of the selected region based on the impedance fluctuation curve specifically includes: obtaining multiple local impedance peaks in the impedance fluctuation curve, and extracting the local contraction frequency of the selected region based on the average time interval of the impedance peaks.

[0020] In conjunction with the first aspect, in certain implementations of the first aspect, using the contraction frequency over-schedule as a control parameter to adjust the output signal frequency of the bioelectrode in the contraction over-schedule region specifically includes:

[0021] The output signal frequency of the bioelectrode in the contraction overshoot region is obtained, and the frequency is proportionally down-clocked according to the contraction frequency overshoot and the preset proportional mapping factor to obtain the corresponding initial pulse frequency.

[0022] The bioelectrode in the contraction overshoot region outputs an electrode signal based on the initial pulse frequency, and detects the contraction frequency overshoot in real time as a feedback factor to correct the initial pulse frequency until the contraction frequency overshoot is within a preset overshoot range.

[0023] In conjunction with the first aspect, in some implementations of the first aspect, the process of superimposing detection pulse signals on the bioelectrode of the selected area includes: acquiring the electrode signal output by the bioelectrode, generating a detection pulse signal based on the pulse frequency and pulse amplitude of the electrode signal, and superimposing the electrode signal and the detection pulse signal for output.

[0024] In conjunction with the first aspect, in some implementations of the first aspect, when the signal linkage characteristic is lower than a preset threshold, the bioelectrode signal is output based on a preset reference signal frequency.

[0025] Secondly, this application provides a localized body sculpting and beauty device based on bioelectricity, which includes a frequency control unit, the frequency control unit comprising:

[0026] The impedance detection module is used to superimpose detection pulse signals on the bioelectrode in the selected area, and perform impedance analysis based on the pulse feedback signal of the detection pulse signals to determine the impedance detection sequence of the selected area.

[0027] The signal processing module is used to construct an impedance fluctuation curve based on the impedance detection sequence, obtain the bioelectric signal of the selected region, perform coupling characteristic analysis based on the bioelectric signal of the selected region and the impedance fluctuation curve, and obtain the signal coupling index.

[0028] The decision module is used to extract the local contraction frequency of the selected area based on the impedance fluctuation curve when the signal linkage characteristics are higher than a preset threshold.

[0029] The signal analysis module is used to determine the symmetrical region of the selected region, extract the symmetrical contraction frequency corresponding to the symmetrical region, and compare the local contraction frequency with the symmetrical contraction frequency to determine the contraction frequency over-schedule of the selected region.

[0030] The frequency adjustment module is used to determine whether the selected region is a contraction overshoot region based on the contraction frequency overshoot, and to adjust the output signal frequency of the bioelectrode in the contraction overshoot region by using the contraction frequency overshoot as a control parameter.

[0031] Thirdly, this application provides a computer terminal device, which includes a memory and a processor. The memory stores code, and the processor is configured to acquire the code and execute the aforementioned control method for a local shaping and beauty instrument based on bioelectricity.

[0032] Fourthly, this application provides a computer-readable storage medium storing at least one computer program, which is loaded and executed by a processor to implement the operations performed by the control method of the bioelectric-based local shaping and beauty device described above.

[0033] The technical solutions provided by the embodiments disclosed in this application have the following beneficial effects:

[0034] This application provides a bioelectric-based local shaping and beauty device and its control method. First, detection pulse signals are superimposed on the bioelectrodes in a selected area. Impedance analysis is then performed based on the pulse feedback signal of the detection pulse signals to determine the impedance detection sequence for the selected area. An impedance fluctuation curve is constructed based on the impedance detection sequence to obtain the bioelectric signal of the selected area. Coupling characteristic analysis is performed based on the bioelectric signal and impedance fluctuation curve of the selected area to obtain a signal coupling index. The local contraction frequency of the selected area is extracted based on the impedance fluctuation curve. A symmetrical region of the selected area is determined, and the corresponding symmetrical contraction frequency is extracted. Symmetrical frequency analysis is performed based on the local contraction frequency and the symmetrical contraction frequency to determine the contraction frequency over-schedule for the selected area. Based on the contraction frequency over-schedule, it is determined whether the selected area is a contraction over-schedule region, and the output signal frequency of the bioelectrodes in the contraction over-schedule region is adjusted accordingly.

[0035] Therefore, this application considers impedance signal fluctuations caused by local muscle contraction. By analyzing the impedance detection sequences of the selected area and its symmetrical area, the contraction response characteristics of each area under the same stimulus are obtained. Based on the coupling characteristics analysis of the impedance fluctuation curve and electromyographic signal, the signal coupling index is calculated to identify the reliability of the impedance fluctuation in representing the contraction activity frequency. Based on the impedance fluctuation, the local contraction frequency and the symmetrical contraction frequency are extracted to determine whether there is an overshoot region of the contraction frequency. The output signal frequency of the bioelectrode in the overshoot region is adjusted in real time to balance the user experience of both sides and improve the comfort of the local shaping and beauty device during use.

[0036] Therefore, it can be seen that this application can adjust the frequency of the pulse current signal based on the impedance fluctuation of both sides, avoid the deviation of the body sensation effect in both sides, and improve the comfort of users of the local shaping beauty device. Attached Figure Description

[0037] Figure 1This is an exemplary flowchart of a control method for a bioelectric-based local body shaping and beauty device, as shown in some embodiments of this application.

[0038] Figure 2 This is a schematic diagram of the structure of a frequency control unit according to some embodiments of this application;

[0039] Figure 3 This is a schematic diagram of the structure of a computer terminal device that implements a control method for a bioelectric-based local shaping and beauty instrument, according to some embodiments of this application. Detailed Implementation

[0040] This application determines the impedance detection sequence of a selected area by superimposing detection pulse signals onto bioelectrodes in the selected region and performing impedance analysis based on the pulse feedback signal of the detection pulse signals. An impedance fluctuation curve is constructed based on the impedance detection sequence to obtain the bioelectrical signal of the selected area. Coupling characteristics are analyzed based on the bioelectrical signal and impedance fluctuation curve of the selected area to obtain a signal coupling index. The local contraction frequency of the selected area is extracted based on the impedance fluctuation curve. A symmetrical region of the selected area is determined, and the corresponding symmetrical contraction frequency is extracted. Symmetrical frequency analysis is performed based on the local contraction frequency and the symmetrical contraction frequency to determine the contraction frequency over-schedule of the selected area. Based on the contraction frequency over-schedule, it is determined whether the selected area is a contraction over-schedule region. The output signal frequency of the bioelectrodes in the contraction over-schedule region is adjusted based on the contraction frequency over-schedule. This method can adjust the pulse current signal frequency based on the impedance fluctuations of both sides of the region, avoiding deviations in the perceived effect between the two sides and improving the user comfort during the use of the local shaping and beauty device.

[0041] To better understand the above technical solutions, a detailed description of the solutions will be provided below in conjunction with the accompanying drawings and specific implementation methods. (Reference) Figure 1 The figure is an exemplary flowchart of a control method for a bioelectric-based local body sculpting and beauty device according to some embodiments of this application. The control method 100 of the bioelectric-based local body sculpting and beauty device mainly includes the following steps:

[0042] In step S101, detection pulse signals are superimposed on the bioelectrode of the selected area, and impedance analysis is performed based on the pulse feedback signal of the detection pulse signals to determine the impedance detection sequence of the selected area.

[0043] Optionally, in some embodiments, the bioelectrode is a patch-type metal foil electrode. The bioelectrode is attached to the skin surface and has good conductivity and contact stability. As those skilled in the art will know, the bioelectrode stimulates muscle tissue by generating a low-potential-difference biomimetic current, thereby accelerating blood circulation and metabolism, achieving the effect of muscle relaxation and soothing the mind and body. The process of using bioelectrodes for biomimetic current stimulation is relatively mature in the prior art. Furthermore, since the bioelectrode in the prior art has its own independent power limiting unit, the biomimetic current it generates is controlled below 2 mA, which will not cause harm to the human body during use.

[0044] Optionally, in some embodiments, the selected area is the skin tissue range covered by the bioelectrodes dynamically selected by the control processor of the local shaping beauty device based on the electrode number of the bioelectrodes. That is, the control processor dynamically selects different bioelectrodes for activation and measurement according to the preset control strategy and real-time feedback information, so that the selected area can cover different parts of the target skin tissue, thereby achieving balanced stimulation of local muscle contraction, blood circulation and skin condition. At the same time, by rotating the selection of different bioelectrodes, local overstimulation can be avoided, improving the safety and uniformity of the user's use process, and providing reliable multi-point data support for impedance monitoring and contraction frequency analysis.

[0045] Optionally, in some embodiments, the process of superimposing detection pulse signals on the bioelectrode in the selected area includes: acquiring the electrode signal output by the bioelectrode, generating a detection pulse signal based on the pulse frequency and pulse amplitude of the electrode signal, and superimposing the electrode signal and the detection pulse signal for output.

[0046] In specific implementation, the electrode signal is the voltage pulse signal output by the bioelectrode itself. It should be noted that directly using the voltage pulse output by the bioelectrode for impedance detection is problematic because the generated stimulation pulse current reaches the milliampere level and the waveform changes rapidly, resulting in nonlinear distortion. Existing medical electrical stimulation devices primarily use high-frequency, small-amplitude measuring currents for gap measurement. At low currents, tissue behaves as an approximately linear conductor, allowing for accurate impedance measurement. In this application, the detection pulse signal is a micro-amplitude electrical signal used for impedance measurement; it is a short, low-amplitude pulse voltage signal with an amplitude much lower than the electrode signal and a frequency that is an integer multiple of the electrode signal. The amplitude and frequency of the detection pulse signal... The rate can be set according to the frequency and amplitude of the electrode signal of the bioelectrode. The corresponding detection pulse signal can be generated according to the preset frequency multiple and amplitude attenuation coefficient. The detection pulse signal is used to act on the tissue without causing muscle contraction, and is used to obtain impedance changes to achieve closed-loop monitoring and control. In specific implementation, the control processor first generates the corresponding detection pulse signal based on the pulse frequency and pulse amplitude of the electrode signal. Through the signal superposition circuit and digital control unit, the detection pulse signal is superimposed with the original electrode signal and output, so that the bioelectrode can perform impedance detection and maintain the stimulation function required by the electrode signal at the same time, realizing the synchronous closed loop of measurement and stimulation.

[0047] Preferably, in some embodiments, the pulse feedback signal is the instantaneous current response sequence corresponding to the high-frequency detection pulse signal acquired by the bioelectrode. Impedance analysis is performed based on the pulse feedback signal of the detection pulse signal to determine the impedance detection sequence for the selected region, specifically including:

[0048] Obtain the instantaneous current response corresponding to each time point in the pulse feedback signal;

[0049] The pulse feedback signal and the detection pulse signal are time-aligned, and the detection impedance is determined based on the instantaneous current response and the voltage amplitude of the detection pulse signal.

[0050] An impedance detection sequence is generated based on the detection impedance at each time point.

[0051] In practice, in order to accurately reflect impedance changes, the sampling rate of the pulse feedback signal is more than 20 times higher than that of the detection pulse signal. During the process of obtaining the pulse feedback signal, bandpass filtering can be used to reduce low-frequency electrode signal interference, and Ohm's law can be used for impedance calculation. This application will not elaborate on these points.

[0052] In step S102, an impedance fluctuation curve is constructed based on the impedance detection sequence to obtain the bioelectric signal of the selected region. Coupling characteristic analysis is performed based on the bioelectric signal of the selected region and the impedance fluctuation curve to obtain the signal coupling index.

[0053] Preferably, in some embodiments, during the process of constructing the impedance fluctuation curve based on the impedance detection sequence, the detection impedance value corresponding to each time point is obtained, and the detection impedance value corresponding to each time point is time-series fitted using a polynomial fitting method to obtain the impedance fluctuation curve.

[0054] Preferably, in some embodiments, during the acquisition of the bioelectric signal of the selected area, a patch-type surface electrode is used to detect the potential difference of the bioelectric signal, and the detected potential difference signal is amplified by a preamplifier to form a continuous voltage time series as the bioelectric signal. It should be noted that the bioelectric signal of the selected area is the electromyographic potential difference signal generated by muscle contraction. Specifically, when muscle cells are stimulated by nerves, action potentials are generated, causing rapid changes in cell membrane potential. When the action potential propagates along the muscle fiber, it causes the flow of ions inside and outside the muscle fiber, thereby forming an electromyographic signal on the skin surface that can be detected by the electrode. Its amplitude is relatively low compared to the output stimulation signal of the bioelectrode. In the actual detection process, since the stimulation pulse signal output by the bioelectrode may interfere with the measurement of the electromyographic signal, in some specific embodiments of this application, the collected electromyographic signal can be band-stop filtered or synchronous filtered according to the pulse frequency of the output signal of the bioelectrode to remove the interference components corresponding to the stimulation pulse frequency. Alternatively, the sampling signal can be temporarily ignored during the output pulse of the bioelectrode, and the electromyographic signal can be collected only during the pulse gap, and the missing signal value can be supplemented by moving average. This application does not specifically limit the signal preprocessing process.

[0055] Preferably, in some embodiments, the signal coupling index is obtained by performing coupling characteristic analysis based on the bioelectrical signal of the selected region and the impedance fluctuation curve, specifically including:

[0056] Extract the signal period from the impedance fluctuation curve;

[0057] Multiple delay times are generated based on the signal period of the impedance fluctuation curve. For any delay, a cross-correlation function is used to calculate the cross-correlation value, and the maximum value of the cross-correlation function is used as the signal coupling index.

[0058] In specific implementation, the coupling characteristics of the impedance fluctuation curve of the selected region and the bioelectrical signal collected in that region are analyzed to obtain the signal coupling index. The specific implementation includes the following steps: First, the periodic features of the impedance fluctuation curve are extracted; for this purpose, the processing unit applies smoothing and denoising processing to the impedance fluctuation curve, and then identifies the continuous fluctuation peak-valley sequence through peak detection, thereby determining the typical period of impedance fluctuation; to improve robustness, a sliding time window averaging can be used in the identification process; the period extraction step can optionally be combined with envelope fitting or polynomial fitting to obtain continuous and smooth period estimation results;

[0059] After obtaining the signal period of the impedance fluctuation curve, multiple delay times are generated based on the identified signal period for coupling analysis. Preferably, the multiple delay times are a set of delay values ​​generated with the impedance period as a reference and a preset step size. For example, the delay time range can be preset to one-fifth to five times the period, with equal intervals totaling 25 delay times, thereby covering the phase difference and time offset between electromyography and impedance. The resolution can be adjusted during the generation of delay times; higher resolution is beneficial for accurately locating the maximum coupling position, but the corresponding computational load increases. In implementation, this application can choose between finer and coarser granularity based on the control processor performance and real-time requirements. For any given delay, the control processor performs a time-sliding comparison between the impedance fluctuation curve and the bioelectric signal aligned with the same time interval under that delay to calculate the similarity metric between the two under that delay condition. The cross-correlation value calculation in the embodiment can be expressed as a process of performing point-to-point product and summation of the sampled values ​​of the two signals within the same time window (other equivalent time-domain similarity assessments can also be used, which are not limited in this application). Before comparison, the two signals can be processed by removing DC components, normalizing amplitude, and standardizing, thereby eliminating the influence of amplitude differences on similarity judgment. Optionally, overlapping windows are used for segmented calculation, and the median statistic of the similarity value of each window is taken as the final similarity metric for the delay.

[0060] After calculating the similarity metric for each preset delay, the control processor selects the maximum value among all similarity metrics corresponding to the delays as the signal coupling index. This maximum value reflects the highest synchronicity or coupling strength between impedance fluctuations and bioelectrical signals within the allowed time offset range. To facilitate subsequent judgment and control, this coupling index can be normalized to a predetermined interval and compared with a preset threshold: when the coupling index is higher than the threshold, it indicates that the impedance fluctuation can reliably reflect muscle electrical activity, and the control processor will allow the use of impedance reference variables for contraction frequency extraction and closed-loop control; when the coupling index is lower than the threshold, the control processor can trigger electrode position reset, signal acquisition parameter adjustment, or prompt manual troubleshooting to ensure measurement reliability. In this embodiment, to ensure timing synchronization and computational stability... To ensure accuracy, the following preferred measures are recommended during implementation: First, ensure that the sampling rate of the impedance fluctuation curve matches that of the bioelectrical signal, or resample and align the two; second, perform bandpass / bandstop filtering and envelope extraction on both signals before coupling analysis to reduce the impact of power frequency interference, motion artifacts, and stimulus artifacts; third, consider device delay and signal propagation lag when generating the delay set, preferably including delays in both positive and negative directions to accommodate cases where impedance leads EMG or EMG leads impedance; fourth, set a minimum reliable window length and a minimum peak amplitude threshold for the coupling index in actual products to avoid misjudgment caused by short-term accidental peaks. Other preprocessing methods to increase the accuracy of signal cross-correlation detection are not listed here, and those skilled in the art can adaptively select them within the feasible range.

[0061] It should be noted that the control processor of this application constructs an impedance fluctuation curve based on the impedance detection sequence and performs correlation characteristic analysis by combining the bioelectric signals collected from the same region's electrodes. By analyzing the time series cross-correlation between impedance fluctuation and electromyographic signals, a signal coupling index is calculated to determine the degree of correlation between muscle activity and impedance changes within the region. When the signal linkage index is higher than a preset threshold, it indicates that the impedance change can effectively reflect the muscle contraction state. At this time, the control processor further extracts the local contraction frequency of the region from the impedance fluctuation curve for the contraction characteristic test of the selected region. Based on the contraction characteristics of the selected region, the output frequency is controlled, thereby improving the regional consistency of the local shaping and beauty device during operation.

[0062] In step S103, when the signal linkage characteristic is higher than a preset threshold, the local contraction frequency of the selected area is extracted based on the impedance fluctuation curve.

[0063] It should be noted that when the bioelectrode of the local shaping beauty device outputs voltage pulses, the contraction frequency of the target muscle group is an important technical indicator for measuring the effect of electrical stimulation. When the contraction frequency of the muscles on both sides is inconsistent during the stimulation process, it often leads to asynchrony between the stimulation intensity and the muscle fiber response, resulting in a left-right deviation in the final therapeutic effect. This affects the overall symmetry experience of the user when using the local shaping beauty device. Muscle contraction makes the fiber direction more orderly and reduces the intercellular space, resulting in a redistribution of the transverse and longitudinal directions. This causes periodic impedance changes during the contraction process. Therefore, the impedance detection sequence of the selected area can be used as data to generate the tissue contraction frequency index corresponding to the selected area.

[0064] Preferably, in some embodiments, when the signal linkage characteristics are lower than a preset threshold, the bioelectrode signal is output based on a preset reference signal frequency. The reference signal frequency is a safe output frequency calibrated through multiple tests. In specific implementation, the current signal output frequency can also be maintained so that the safe frequency range is maintained when impedance fluctuations cannot reflect muscle contraction characteristics. Users can also make adaptive signal adjustments based on their own feelings within the safe threshold range.

[0065] Preferably, in some embodiments, extracting the local contraction frequency of the selected region based on the impedance fluctuation curve specifically includes: obtaining multiple local impedance peaks in the impedance fluctuation curve, and extracting the local contraction frequency of the selected region based on the average time interval of the impedance peaks. Specifically, the constructed impedance fluctuation curve is traversed to identify multiple local impedance peaks that appear in the time dimension. To avoid interference from spurious peaks caused by noise, the impedance fluctuation curve can be smoothed, thresholded, or compared with neighboring regions to retain only peaks with significant amplitude, stable morphology, and physiological change characteristics. Then, all the obtained effective peaks are arranged in chronological order, and the time interval between two adjacent peaks is calculated. Since impedance fluctuation reflects the tissue density change of the muscle during a complete contraction, the peak time interval can correspond to the rhythmic change of muscle contraction. After determining the time interval of all peaks, these intervals can be statistically analyzed, for example, by taking the average of multiple intervals to obtain the average contraction cycle of the selected region within that time period. This average contraction cycle is used to characterize the overall contraction rhythm of the local muscle, avoiding errors caused by instantaneous jitter at a single interval point. Finally, the local contraction frequency of the selected region is determined by taking the reciprocal of the average contraction cycle.

[0066] In step S104, a symmetrical region of the selected region is determined, the symmetrical contraction frequency corresponding to the symmetrical region is extracted, and the local contraction frequency is compared with the symmetrical contraction frequency to determine the contraction frequency over-schedule of the selected region.

[0067] Preferably, in some embodiments, the control processor mounted on the local shaping and beauty device obtains the corresponding numbers of the bioelectrodes contained in the selected area and the symmetrical area, determines the symmetrical electrode corresponding to the symmetrical area of ​​the selected area, and extracts the impedance fluctuation curve of the symmetrical electrode to generate the symmetrical contraction frequency.

[0068] In specific implementation, the control processor connected to the local body sculpting device obtains the corresponding numbers of the bioelectrodes contained in the selected area and the symmetrical area. Based on a preset electrode layout model, the control processor maps each electrode number to its corresponding skin coverage area, automatically selecting electrode groups that are spatially mirror-image or symmetrically related to the selected area. The symmetrical area of ​​the selected area is then determined, and the corresponding symmetrical electrode is obtained. The symmetrical contraction frequency can be obtained using the same method as the local contraction frequency. After obtaining the symmetrical electrode, the control processor performs the same impedance detection process as for the selected area on the symmetrical electrode, detecting the pulse signal... The pulse feedback signal constructs a corresponding impedance detection sequence and further generates the impedance fluctuation curve of the symmetrical electrode. Subsequently, the control processor extracts the impedance peak set of the symmetrical region based on the distribution of impedance peaks in the impedance fluctuation curve, and determines the symmetrical contraction frequency corresponding to the symmetrical region based on the average time interval between adjacent impedance peaks. The extraction method of the symmetrical contraction frequency is consistent with the extraction process of the local contraction frequency of the selected region, including peak identification, time interval statistics, and periodic change analysis. This application will not elaborate on this further. Those skilled in the art can directly obtain the frequency characteristics of the symmetrical region by implementing the selected region frequency extraction method according to the specification.

[0069] Preferably, in some embodiments, during the process of determining the contraction frequency overschedule corresponding to the selected region by comparing the local contraction frequency with the symmetrical contraction frequency, the frequency ratio of the local contraction frequency to the symmetrical contraction frequency is used as the contraction frequency overschedule corresponding to the selected region. The contraction frequency overschedule can be used to characterize the degree of bilateral somatosensory difference caused by muscle contraction. Specifically, since symmetrical regions cover the muscle tissues that are opposite to each other on the left and right or front and back of the human body, their contraction rhythms should be consistent under normal stimulation. Therefore, when excessive contraction or uneven stimulation occurs in a local area, the contraction frequencies of the two will show a significant difference. To address the issue of sensory differences, this embodiment uses the ratio of local contraction frequency to symmetrical contraction frequency as a measure of the degree of contraction deviation in the selected area, representing the contraction frequency overschedule. When this ratio deviates from a preset physiological range, such as approaching the equilibrium range of 1, it indicates that the selected area has a significant contraction overschedule relative to its symmetrical area. The control processor can then determine whether stimulation compensation or weakening adjustment is needed for this area based on the contraction frequency overschedule. This enables dynamic balance monitoring of corresponding muscle areas on the left and right or front and back without adding additional hardware, giving the electrical stimulation output adaptive adjustment capabilities and effectively avoiding bilateral sensory differences caused by excessive unilateral stimulation.

[0070] In step S105, the selected region is determined to be a contraction overshoot region based on the contraction frequency overschedule, and the contraction frequency overschedule is used as a control parameter to adjust the output signal frequency of the bioelectrode in the contraction overshoot region.

[0071] Preferably, in some embodiments, the process of determining whether the selected region is a shrinkage overshoot region based on the shrinkage frequency overschedule specifically includes: determining whether the shrinkage frequency overschedule belongs to a preset overshoot interval range; if it is higher than the interval range, the selected region is determined to be a shrinkage overshoot region; if it is lower than the interval range, the symmetrical region of the selected region is determined to be a shrinkage overshoot region.

[0072] In specific implementation, after acquiring the contraction frequency overshoot, the control processor first compares the contraction frequency overshoot with a frequency judgment interval preset by the control processor. The overshoot interval is preset by empirical data, and its upper and lower limits are fixed constant values ​​used to characterize the normal and balanced bilateral muscle contraction state. When the contraction frequency overshoot is higher than the upper limit of the overshoot interval, it indicates that the muscle contraction frequency of the selected area is significantly higher than that of the symmetrical area, that is, the area shows a strong response or over-contraction trend during the current bioelectric stimulation. Based on this, the control processor marks the selected area as a contraction overshoot area and enters the subsequent output adjustment process. When the contraction frequency overshoot is lower than the lower limit of the overshoot interval, it indicates that the contraction amplitude or frequency of the symmetrical area is significantly higher, while the selected area is under-responsive during contraction. In order to maintain the bilateral contraction balance, the control processor determines the symmetrical area as a contraction overshoot area and adjusts the bioelectric output corresponding to the area. When the contraction frequency overshoot is within the overshoot interval, it indicates that the contraction frequency of the muscles on both sides is in a basically balanced state. At this time, the control processor determines that there is no contraction overshoot area and maintains the existing bioelectric output strategy.

[0073] Preferably, in some embodiments, using the contraction frequency over-schedule as a control parameter to adjust the output signal frequency of the bioelectrode in the contraction over-schedule region specifically includes:

[0074] The output signal frequency of the bioelectrode in the contraction overshoot region is obtained, and the frequency is proportionally down-clocked according to the contraction frequency overshoot and the preset proportional mapping factor to obtain the corresponding initial pulse frequency.

[0075] The bioelectrode in the contraction overshoot region outputs an electrode signal based on the initial pulse frequency, and detects the contraction frequency overshoot in real time as a feedback factor to correct the initial pulse frequency until the contraction frequency overshoot is within a preset overshoot range.

[0076] In practice, a frequency mapping table is pre-stored in the control processor. This frequency mapping table maps the contraction frequency overschedule of different ranges to the corresponding initial pulse frequency level. When a contraction frequency overschedule of a selected area is detected, the control unit reads the mapping table and determines the initial pulse frequency of the area as the first adjustment value based on the size of the overschedule and the preset proportional mapping factor. The mapping strategy can determine the corresponding level of tissue, such as fine adjustment, medium adjustment and emphasis adjustment. Each adjustment level has its corresponding frequency adjustment ratio. The initial pulse frequency is determined based on the frequency adjustment ratio and the output frequency of the bioelectrode in the contraction overschedule area. The control unit sends the initial pulse frequency to the bioelectrode in the contraction overschedule area so that it outputs the electrode signal at the frequency to continue to apply biomimetic stimulation to the tissue.

[0077] The system continues to inject detection pulses and collect pulse feedback in parallel using a preset measurement strategy, thereby continuously updating the impedance fluctuation curve and re-extracting the current local contraction frequency and contraction frequency overschedule as real-time feedback factors. The control unit compares the new overschedule value calculated in real time with the target overschedule interval (i.e., the desired overschedule interval): if the current overschedule is already within the preset target interval, it maintains or smoothly transitions to that frequency and does not continue to increase / decrease; if the target interval has not yet been reached, the next frequency correction is performed according to the preset correction strategy. The preferred correction strategy is to adjust the proportional mapping factor and combine it with a gradually converging step size. The feedback is observed again after each correction until the overschedule enters the target interval or the maximum number of iterations is reached.

[0078] Preferably, in some embodiments, to avoid muscle overstimulation or control oscillation caused by rapid frequency switching, the frequency adjustment in the embodiments adopts a gradual rise and fall and hysteresis mechanism: frequency changes are performed smoothly at a limited rate (such as several small changes), and a more conservative adjustment strategy is triggered or further adjustment is paused when a reversal of the overschedule direction or an oscillation trend is detected, until the signal stabilizes; the control unit also maintains the history of the most recent overschedule and frequency values ​​to determine the convergence trend and decide whether to continue iterating. Preset safety constraints are used in any correction process, including but not limited to: the maximum / minimum frequency boundary of electrode output, the maximum allowable current / voltage, the cumulative stimulation time limit of a single region, and the forced stop of the electrode power limiting unit. If any safety threshold is triggered, the control unit immediately stops the output and issues an alarm, or returns to the previous safe state.

[0079] It should be noted that, under the condition that the signal amplitude remains unchanged, this application adjusts the output signal frequency of the bioelectrode in the selected area by over-scheduling the contraction frequency, thereby reducing the energy output of the bioelectrode and achieving efficient signal control. This causes the frequency of independent muscle contraction with each signal pulse to decrease. At the same time, the system monitors the selected area and its corresponding symmetrical area in real time. Through impedance fluctuation curves and electromyographic signals, it extracts the local contraction frequency and symmetrical contraction frequency, and performs closed-loop feedback adjustment based on the contraction frequency over-scheduling, thereby dynamically balancing the muscle contraction frequency in different areas, avoiding deviation in the perceived effect between the two sides, and improving the comfort of users of the local shaping and beauty device.

[0080] In another aspect, in some embodiments, this application provides a bioelectric-based local body sculpting and beauty device, the system including a frequency control unit, referenced... Figure 2The figure is a schematic diagram of the exemplary hardware and / or software structure of a frequency control unit according to some embodiments of this application. The frequency control unit 200 includes: an impedance detection module 201, a signal processing module 202, a decision module 203, a signal analysis module 204, and a frequency adjustment module 205, which are described below:

[0081] Impedance detection module 201 is used to superimpose detection pulse signals on the bioelectrode of the selected area, and perform impedance analysis based on the pulse feedback signal of the detection pulse signals to determine the impedance detection sequence of the selected area.

[0082] Signal processing module 202 is used to construct an impedance fluctuation curve based on the impedance detection sequence, obtain the bioelectric signal of the selected region, perform coupling characteristic analysis based on the bioelectric signal of the selected region and the impedance fluctuation curve, and obtain signal coupling index.

[0083] Decision module 203 is used to extract the local contraction frequency of the selected area based on the impedance fluctuation curve when the signal linkage characteristics are higher than a preset threshold.

[0084] Signal analysis module 204 is used to determine the symmetrical region of the selected region, extract the symmetrical contraction frequency corresponding to the symmetrical region, and determine the contraction frequency over-schedule corresponding to the selected region by comparing the local contraction frequency with the symmetrical contraction frequency.

[0085] The frequency adjustment module 205 is used to determine whether the selected region is a contraction overshoot region based on the contraction frequency overshoot, and to adjust the output signal frequency of the bioelectrode in the contraction overshoot region by using the contraction frequency overshoot as a control parameter.

[0086] The foregoing has provided a detailed example of a local shaping and beauty device based on bioelectricity and its control method provided in the embodiments of this application. It is understood that, in order to achieve the above functions, the corresponding device includes hardware structures and / or software modules for performing each function.

[0087] Those skilled in the art should readily recognize that, based on the units and algorithm steps of the various examples described in conjunction with the embodiments disclosed herein, this application can be implemented in hardware or a combination of hardware and computer software. Whether a certain function in the application is executed in a manner that drives hardware or computer software depends on the specific application and design constraints of the technical solution. Therefore, those skilled in the art can use different methods to implement the described function for each specific application, but such implementation should not be considered to be beyond the scope of this application.

[0088] In addition, this application also provides a computer terminal device, which includes a memory and a processor. The memory stores code, and the processor is configured to acquire the code and execute the above-described control method for a local shaping and beauty instrument based on bioelectricity.

[0089] In some embodiments, reference Figure 3 The figure is a schematic diagram of the structure of a computer terminal device implementing a control method for a bioelectric-based local body sculpting and beauty device according to some embodiments of this application; the control method for a bioelectric-based local body sculpting and beauty device in the above embodiments can be achieved through... Figure 3 The computer terminal device 300 shown is used to implement this, and the computer terminal device 300 includes at least one communication bus 301, communication interface 302, processor 303 and memory 304.

[0090] The processor 303 may be a general-purpose central processing unit (CPU), an application-specific integrated circuit (ASIC), or one or more devices used to control the execution of a control method for a bioelectric-based local shaping and beauty device as described in this application.

[0091] The communication bus 301 may include a path for transmitting information between the aforementioned components.

[0092] The memory 304 may be a read-only memory (ROM) or other type of static storage device capable of storing static information and instructions, random access memory (RAM) or other type of dynamic storage device capable of storing information and instructions, or electrically erasable programmable read-only memory (EEPROM), compact disc read-only memory (CD-ROM) or other optical disc storage, optical disc storage (including compressed optical discs, laser discs, optical discs, digital universal optical discs, Blu-ray discs, etc.), magnetic disks or other magnetic storage devices, or any other medium capable of carrying or storing desired program code in the form of instructions or data structures and accessible by a computer, but not limited thereto; the memory 304 may exist independently and be connected to the processor 303 via the communication bus 301; the memory 304 may also be integrated with the processor 303.

[0093] The memory 304 stores program code that executes the scheme of this application, and its execution is controlled by the processor 303. The processor 303 executes the program code stored in the memory 304. The program code may include one or more software modules. In the above embodiments, the determination of the signal coupling index can be achieved by the processor 303 and one or more software modules in the program code in the memory 304.

[0094] Communication interface 302 uses any transceiver-like device for communicating with other devices or communication networks, such as Ethernet, radio access network (RAN), wireless local area network (WLAN), etc.

[0095] Optionally, the computer terminal device 300 may also include a power supply 305 for providing power to various devices or circuits in the real-time computer terminal device.

[0096] In a specific implementation, as one example, a computer terminal device may include multiple processors, each of which may be a single-core (single-CPU) processor or a multi-core (multi-CPU) processor. Here, a processor may refer to one or more devices, circuits, and / or processing cores used to process data (e.g., computer program instructions).

[0097] The aforementioned computer terminal device can be a general-purpose computer terminal device or a dedicated computer terminal device. In specific implementations, the computer terminal device can be a desktop computer, a portable computer, a network server, a handheld digital assistant (PDA), a mobile phone, a tablet computer, a wireless terminal device, a communication device, or an embedded device. This application does not limit the type of computer terminal device.

[0098] In addition, other aspects of this application provide a computer-readable storage medium storing at least one computer program, which is loaded and executed by a processor to perform the operations performed by the control method of the bioelectric-based local shaping and beauty device described above.

[0099] In summary, the local shaping and beauty device and its control method based on bioelectricity disclosed in this application involve superimposing detection pulse signals on the bioelectrodes of a selected area, performing impedance analysis based on the pulse feedback signal of the detection pulse signals to determine the impedance detection sequence of the selected area; constructing an impedance fluctuation curve based on the impedance detection sequence to obtain the bioelectric signal of the selected area; performing coupling characteristic analysis based on the bioelectric signal and impedance fluctuation curve of the selected area to obtain the signal coupling index; extracting the local contraction frequency of the selected area based on the impedance fluctuation curve; determining the symmetrical region of the selected area, extracting the corresponding symmetrical contraction frequency of the symmetrical region, performing symmetrical frequency analysis based on the local contraction frequency and the symmetrical contraction frequency to determine the contraction frequency over-schedule of the selected area; determining whether the selected area is a contraction over-schedule region based on the contraction frequency over-schedule, and adjusting the output signal frequency of the bioelectrodes in the contraction over-schedule region based on the contraction frequency over-schedule. This method can adjust the pulse current signal frequency based on the impedance fluctuation of both sides of the region, avoiding deviation in the perceived effect between the two sides of the region and improving the user comfort during the use of the local shaping and beauty device.

[0100] The above descriptions are merely embodiments of this application, and common knowledge such as specific technical solutions or characteristics in the solutions are not described in detail here. It should be noted that those skilled in the art can make several modifications and improvements without departing from the technical solutions of this application, and these should also be considered within the scope of protection of this application, without affecting the effectiveness of the implementation of this application or the practicality of the patent.

[0101] The scope of protection claimed in this application shall be determined by the content of its claims. The specific embodiments described in the specification can be used to interpret the content of the claims. Obviously, those skilled in the art can make various modifications and variations to this application without departing from the spirit and scope of the invention. Therefore, if these modifications and variations of this application fall within the scope of the claims of this application and their equivalents, this application also intends to include these modifications and variations.

Claims

1. A control method for a localized body sculpting and beauty device based on bioelectricity, characterized in that, include: The method of superimposing detection pulse signals on a selected area of ​​bioelectrode specifically includes: acquiring the electrode signal output by the bioelectrode, generating a detection pulse signal based on the pulse frequency and pulse amplitude of the electrode signal, and superimposing and outputting the electrode signal and the detection pulse signal; performing impedance analysis based on the pulse feedback signal of the detection pulse signal to determine the impedance detection sequence of the selected area; An impedance fluctuation curve is constructed based on the impedance detection sequence to obtain the bioelectrical signal of the selected region. Coupling characteristic analysis is then performed based on the bioelectrical signal of the selected region and the impedance fluctuation curve to obtain signal coupling indices, specifically including: Extract the signal period from the impedance fluctuation curve; Multiple delay times are generated based on the signal period of the impedance fluctuation curve. For any delay, a cross-correlation function is used to calculate the cross-correlation value, and the maximum value of the cross-correlation function is used as the signal coupling index. When the signal linkage characteristic is higher than a preset threshold, the local contraction frequency of the selected area is extracted based on the impedance fluctuation curve. Determine the symmetrical region of the selected region, extract the symmetrical contraction frequency corresponding to the symmetrical region, and perform over-schedule comparison between the local contraction frequency and the symmetrical contraction frequency to determine the over-schedule of the contraction frequency corresponding to the selected region. Based on the contraction frequency overschedule, it is determined whether the selected region is a contraction overschedule region, and the contraction frequency overschedule is used as a control parameter to adjust the output signal frequency of the bioelectrode in the contraction overschedule region.

2. The method as described in claim 1, characterized in that, Impedance analysis is performed based on the pulse feedback signal of the detected pulse signal to determine the impedance detection sequence of the selected region, which specifically includes: Obtain the instantaneous current response corresponding to each time point in the pulse feedback signal; The pulse feedback signal and the detection pulse signal are time-aligned, and the detection impedance is determined based on the instantaneous current response and the voltage amplitude of the detection pulse signal. An impedance detection sequence is generated based on the detection impedance at each time point.

3. The method as described in claim 1, characterized in that, Extracting the local contraction frequency of the selected region based on the impedance fluctuation curve specifically includes: obtaining multiple local impedance peaks in the impedance fluctuation curve, and extracting the local contraction frequency of the selected region based on the average time interval of the impedance peaks.

4. The method as described in claim 1, characterized in that, Using the contraction frequency overshoot as a control parameter, adjusting the output signal frequency of the bioelectrode in the contraction overshoot region specifically includes: The output signal frequency of the bioelectrode in the contraction overshoot region is obtained, and the frequency is proportionally down-clocked according to the contraction frequency overshoot and the preset proportional mapping factor to obtain the corresponding initial pulse frequency. The bioelectrode in the contraction overshoot region outputs an electrode signal based on the initial pulse frequency, and detects the contraction frequency overshoot in real time as a feedback factor to correct the initial pulse frequency until the contraction frequency overshoot is within a preset overshoot range.

5. The method as described in claim 1, characterized in that, When the signal linkage characteristic is lower than the preset threshold, the bioelectrode signal is output based on the preset reference signal frequency.

6. A bioelectric-based local body sculpting and beauty device, comprising a frequency control unit, wherein the frequency control unit is used to execute the control method of the bioelectric-based local body sculpting and beauty device according to any one of claims 1 to 5, characterized in that, The frequency control unit includes: The impedance detection module is used to superimpose detection pulse signals on the bioelectrode in the selected area, and perform impedance analysis based on the pulse feedback signal of the detection pulse signals to determine the impedance detection sequence of the selected area. The signal processing module is used to construct an impedance fluctuation curve based on the impedance detection sequence, obtain the bioelectric signal of the selected region, perform coupling characteristic analysis based on the bioelectric signal of the selected region and the impedance fluctuation curve, and obtain the signal coupling index. The decision module is used to extract the local contraction frequency of the selected area based on the impedance fluctuation curve when the signal linkage characteristics are higher than a preset threshold. The signal analysis module is used to determine the symmetrical region of the selected region, extract the symmetrical contraction frequency corresponding to the symmetrical region, and compare the local contraction frequency with the symmetrical contraction frequency to determine the contraction frequency over-schedule of the selected region. The frequency adjustment module is used to determine whether the selected region is a contraction overshoot region based on the contraction frequency overshoot, and to adjust the output signal frequency of the bioelectrode in the contraction overshoot region by using the contraction frequency overshoot as a control parameter.

7. A computer terminal device, characterized in that, The computer terminal device includes a memory and a processor. The memory stores code, and the processor is configured to acquire the code and execute a control method for a bioelectric-based local shaping and beauty device as described in any one of claims 1 to 5.

8. A computer-readable storage medium storing at least one computer program, characterized in that, The computer program is loaded and executed by a processor to perform the operations described in any one of claims 1 to 5 of the control method for a bioelectric-based local shaping and beauty device.

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