Electrical stimulation system, method and electronic device

Abstract

This application discloses an electrical stimulation system, method, and electronic device, comprising: a sensing component configured to acquire working signals characterizing changes in uterine electromyographic activity, and to perform feature analysis on the working signals to generate working parameters characterizing the current state and trend of uterine contractions; a control component wirelessly connected to the sensing component; a first stimulation electrode and a second stimulation electrode, respectively connected to the control component; the control component configured to identify the current state of uterine electromyographic activity and its state transition trend based on the working parameters, and to determine a target electrical stimulation strategy based on the state of uterine electromyographic activity and its state transition trend, generating a target electrical stimulation signal, and synchronously outputting the target electrical stimulation signal through a single-channel drive of the first and second stimulation electrodes. Thus, the target electrical stimulation signal can be adaptively adjusted according to changes in uterine contraction activity, improving the matching degree between the labor analgesia stimulation output and the actual uterine contraction rhythm.

Description

Technical Field

[0001] This application relates to the technical field of medical devices, and more specifically, to an electrical stimulation system, method, and electronic device. Background Technology

[0002] In the field of labor analgesia, transcutaneous electrical nerve stimulation (TENS) is a commonly used non-pharmacological analgesia method. It works by activating the gate control mechanism of the dorsal horn of the spinal cord through low-frequency pulsed current, inhibiting pain signal transmission, and promoting the release of endogenous opioid peptides, thereby reducing pain perception.

[0003] In related technologies, electrical stimulation systems mostly adjust stimulation parameters based on the presence or absence of uterine contractions, the intensity of a single contraction, or a fixed threshold. This makes it difficult to reflect the continuous migration of uterine myoelectric activity during labor, and it is also difficult to achieve smooth switching and cumulative stimulation control during the strengthening, peak, decline, and recovery of uterine contractions. As a result, the output stimulation does not match the actual uterine contraction rhythm and pain changes of the parturient. Summary of the Invention

[0004] In view of the above problems, this application proposes an electrical stimulation system, method and electronic device that can solve the above problems.

[0005] In a first aspect, embodiments of this application provide an electrical stimulation system, comprising: a sensing component configured to acquire working signals characterizing changes in the state of uterine electromyography (UEEMG), and to perform feature analysis on the working signals to generate working parameters characterizing the current state and trend of uterine contractions; a control component wirelessly connected to the sensing component; a first stimulation electrode and a second stimulation electrode respectively connected to the control component; and a control component configured to identify the current state of uterine EEMG and its state transition trend based on the working parameters, determine a target electrical stimulation strategy based on the state of uterine EEMG and its state transition trend, generate a target electrical stimulation signal, and synchronously output the target electrical stimulation signal through a single channel driving the first and second stimulation electrodes.

[0006] Secondly, embodiments of this application also provide an electrical stimulation method, which includes: acquiring working signals characterizing changes in the state of uterine myoelectric activity; performing feature analysis on the working signals to generate working parameters characterizing the current state and trend of uterine contraction activity; identifying the current state of uterine myoelectric activity and its state transition trend based on the working parameters; determining a target electrical stimulation strategy based on the state of uterine myoelectric activity and its state transition trend; generating a target electrical stimulation signal; and synchronously outputting the target electrical stimulation signal through a single-channel drive of a first stimulation electrode and a second stimulation electrode.

[0007] Thirdly, embodiments of this application also provide an electronic device, including a processor, a memory, and one or more application programs; the one or more application programs are stored in the memory and configured to be executed by the processor to implement the above-described electrostimulation method.

[0008] The technical solution provided in this application includes an electrical stimulation system comprising: a sensing component configured to acquire working signals characterizing changes in uterine electromyographic activity, and to perform feature analysis on the working signals to generate working parameters characterizing the current state and trend of uterine contractions; a control component wirelessly connected to the sensing component; a first stimulation electrode and a second stimulation electrode, respectively connected to the control component; and a control component configured to identify the current state of uterine electromyographic activity and its transition trend based on the working parameters, determine a target electrical stimulation strategy based on the state of uterine electromyographic activity and its transition trend, generate a target electrical stimulation signal, and synchronously output the target electrical stimulation signal through a single-channel drive of the first and second stimulation electrodes. Thus, by acquiring working signals characterizing changes in uterine electromyographic activity and performing feature analysis to generate working parameters, and then identifying the state of uterine electromyographic activity and its transition trend based on the working parameters, a target electrical stimulation strategy matching the current state of uterine contractions is determined. This enables the target electrical stimulation signal to adaptively adjust with changes in uterine contraction intensity, peak value, decline, or recovery, thereby improving the matching degree between the analgesic stimulation output and the actual uterine contraction rhythm and pain changes in the parturient. Attached Figure Description

[0009] To more clearly illustrate the technical solutions in the embodiments of this application, the accompanying drawings used in the description of the embodiments will be briefly introduced below. Obviously, the drawings described below are only some embodiments of this application, and not all embodiments. Based on the embodiments of this application, all other embodiments and drawings obtained by those skilled in the art without creative effort are within the scope of protection of this invention.

[0010] Figure 1 A schematic diagram of the structure of an electrical stimulation system according to an embodiment of this application is shown.

[0011] Figure 2 A schematic diagram of the structure of a sensing component according to an embodiment of this application is shown.

[0012] Figure 3 A schematic diagram of another electrical stimulation system according to an embodiment of this application is shown.

[0013] Figure 4 A schematic flowchart of an electrical stimulation method provided in an embodiment of this application is shown.

[0014] Figure 5A schematic diagram of the structure of an electronic device provided in an embodiment of this application is shown.

[0015] Figure 6 This illustration shows a schematic diagram of the structure of a computer-readable storage medium provided in an embodiment of this application. Detailed Implementation

[0016] Exemplary embodiments will now be described in detail, examples of which are illustrated in the accompanying drawings. When the following description relates to the drawings, unless otherwise indicated, the same numerals in different drawings denote the same or similar elements. The embodiments described in the following exemplary embodiments do not represent all embodiments consistent with the present invention. Rather, they are merely examples of apparatuses and methods consistent with some aspects of the invention as detailed in the appended claims.

[0017] It should be understood that the specific embodiments described herein are merely illustrative of the invention and are not intended to limit the invention.

[0018] It should be understood that, when used in this application specification and the appended claims, the term "comprising" indicates the presence of the described features, integrals, steps, operations, elements and / or components, but does not exclude the presence or addition of one or more other features, integrals, steps, operations, elements, components and / or a collection thereof.

[0019] It should also be understood that the term “and / or” as used in this application specification and the appended claims means any combination of one or more of the associated listed items and all possible combinations, and includes such combinations.

[0020] Furthermore, in the description of this application and the appended claims, the terms "first," "second," "third," etc., are used only to distinguish descriptions and should not be construed as indicating or implying relative importance.

[0021] References to "one embodiment" or "some embodiments" in this specification mean that one or more embodiments of this application include a specific feature, structure, or characteristic described in connection with that embodiment. Therefore, the phrases "in one embodiment," "in some embodiments," "in other embodiments," "in still other embodiments," etc., appearing in different parts of this specification do not necessarily refer to the same embodiment, but rather mean "one or more, but not all, embodiments," unless otherwise specifically emphasized.

[0022] Please see Figure 1 , Figure 1 A schematic diagram of the structure of an electrical stimulation system according to an embodiment of this application is shown, as follows: Figure 1As shown, the electrical stimulation system 100 includes a sensing component 110, a control component 120, a first stimulation electrode 130, and a second stimulation electrode 140.

[0023] The sensing component 110 is configured to acquire working signals characterizing changes in the state of uterine electromyography (UEEMG) activity, perform feature analysis on the working signals, and generate working parameters characterizing the current state and trend of uterine contractions. The control component 120 is wirelessly connected to the sensing component 110. The first stimulation electrode 130 and the second stimulation electrode 140 are respectively connected to the control component 120. The control component 120 is configured to identify the current state of uterine EEMG activity and its state transition trend based on the working parameters, determine the target electrical stimulation strategy based on the state of uterine EEMG activity and its state transition trend, generate the target electrical stimulation signal, and drive the first stimulation electrode 130 and the second stimulation electrode 140 to synchronously output the target electrical stimulation signal through a single channel.

[0024] The sensing component 110 is a wireless acquisition unit independent of the control component 120. It is configured to fit against the fundus of the user's abdomen. The sensing component 110 can acquire raw uterine electromyography signals (i.e., working signals) and filter, amplify and analyze the raw uterine electromyography signals to generate working parameters that can characterize the current uterine contraction activity status and trend of change, and then transmit them to the control component 120 wirelessly.

[0025] In some implementations, the sensing component 110 is used only for identifying the intensity of uterine contractions, and does not participate in the monitoring of other physiological parameters such as fetal heart rate or maternal heart rate, thereby avoiding signal interference caused by multi-parameter monitoring, significantly improving the accuracy of working signal identification, and ensuring the accuracy of subsequent electrical stimulation regulation.

[0026] In one specific embodiment, the sensing component 110 may be an abdominal electromyography (EMG) detection patch. Specifically, in some embodiments, please refer to... Figure 2 , Figure 2 A schematic diagram of the structure of a sensing component 110 according to an embodiment of this application is shown, as follows: Figure 2 As shown, the sensing component 110 includes differential electromyography electrodes 111, a microcontroller 112, and a wireless communication module 113.

[0027] The differential electromyography electrode 111 is configured to acquire working signals; the microcontroller 112 is configured to perform feature analysis on the working signals and generate working parameters; and the wireless communication module 113 is wirelessly connected to the control component 120 and is configured to send the working parameters to the control component 120.

[0028] The differential electromyography electrode 111 is used to acquire raw uterine electromyography signals as working signals. The differential electrode structure can effectively suppress common-mode interference and improve the acquisition quality of weak electromyography signals.

[0029] The microcontroller 112 is connected to the differential electromyography electrode 111, and the sensing component 110 also includes a signal filtering and amplification unit. The microcontroller 112 is configured to acquire the working signal processed by the signal filtering and amplification unit.

[0030] The microcontroller 112 has a pre-built uterine contraction intensity recognition algorithm and is configured to perform feature analysis on the working signal. For example, the microcontroller 112 calculates at least one feature quantity among the signal envelope, peak value, and duration of the working signal using a time-domain analysis algorithm, and converts it into working parameters characterizing the current uterine contraction activity state and its changing trend. By integrating signal processing and feature extraction functions onto a separate patch on the abdomen, losses and interference during the transmission of the original analog signal can be reduced, improving the accuracy of uterine contraction recognition.

[0031] The wireless communication module 113 is connected to the microcontroller 112 and configured to establish a wireless communication connection with the control component 120. The wireless communication module 113 wirelessly transmits the operating parameters generated by the microcontroller 112 to the control component 120 in real time, so as to support the control component 120 to automatically switch the electrical stimulation mode and adjust the parameters according to the operating parameters.

[0032] In one specific implementation, the wireless communication module 113 integrates a Bluetooth radio frequency unit and a baseband controller. After the microcontroller 112 generates operating parameters, it packages and sends the operating parameters to the corresponding Bluetooth receiver of the control component 120 via Bluetooth broadcast or connection channel. In another specific implementation, the wireless communication module 113 can also be implemented using other short-range wireless communication technologies, such as a ZigBee module, a Wi-Fi module, or a 433MHz radio frequency module.

[0033] In some embodiments, the sensing component 110 also includes a micro battery and a power button. The built-in micro battery eliminates the need for the sensing component 110 to be connected to an external power source or control component 120 via physical wires, thus achieving wireless and independent operation. This significantly improves user comfort and freedom of movement while wearing the device, avoiding the inconvenience of tangled cables.

[0034] The power button is located on the side wall or surface of the sensing component 110 and is electrically connected to the microcontroller 112. The power button is configured to receive a user's trigger operation and generate a power-on signal to be sent to the microcontroller 112. In response to the power-on signal, the microcontroller 112 powers on the control signal filtering and amplification unit, the wireless communication module 113, and other structures, starts collecting working signals, and establishes a wireless connection with the control component 120.

[0035] In one specific implementation, the power button can be a touch switch or a touch-sensitive button to reduce size and improve ease of operation.

[0036] Furthermore, in some embodiments, the sensing component 110 is configured to: filter and amplify the working signal to obtain a processed working signal; extract the envelope of the processed working signal to obtain a uterine contraction waveform envelope curve; determine the state of the uterine contraction waveform envelope curve based on a preset rising edge trigger threshold and a preset falling edge end threshold, and determine the start time and end time; obtain the burst wave duration based on the time difference between the start time and the end time; extract the maximum amplitude of the uterine contraction waveform envelope curve within the time window between the start time and the end time, and use it as the peak intensity of the current uterine contraction; and determine the working parameters based on the burst wave duration, peak intensity, signal change trend, and / or uterine contraction rhythm information per unit time.

[0037] In embodiments of this application, the signal change trend includes parameters characterizing the enhancement, peak maintenance, or decline of uterine electromyography signals, and the unit time uterine contraction rhythm information includes contraction interval and / or contraction density.

[0038] Since the original uterine electromyography signal (i.e., the working signal) is usually weak and mixed with power frequency interference, baseline drift and other noise, the microcontroller 112 or the signal filtering and amplification module in conjunction with the front end is configured to perform bandpass filtering on the working signal to remove high-frequency noise and low-frequency drift, and to perform gain amplification, so as to obtain a processed working signal with a higher signal-to-noise ratio.

[0039] To visually characterize the intensity change trend of uterine contractions, the microcontroller 112 extracts the envelope of the processed working signal. For example, it can extract the uterine contraction waveform envelope curve that reflects the energy change of uterine muscle contraction by calculating the moving root mean square of the signal or by using Hilbert transform. The uterine contraction waveform envelope curve can smooth out the high-frequency jitter in the electromyographic signal.

[0040] In order to accurately identify a complete uterine contraction event, the microcontroller 112 performs real-time scanning and status determination of the uterine contraction waveform envelope curve based on a preset rising edge trigger threshold and a preset falling edge end threshold.

[0041] Optionally, the preset rising edge trigger threshold and the preset falling edge end threshold can be empirical values ​​obtained from clinical trial data and pre-programmed into the memory of the microcontroller 112. For example, considering the typical amplitude range of uterine electromyography signals during the rupture phase of uterine contractions, the preset rising edge trigger threshold can be set to a first voltage value, and the preset falling edge end threshold can be set to a second voltage value. The first voltage value is greater than the second voltage value.

[0042] Optionally, during the initial activation of the electrical stimulation system 100 or the interval between two uterine contractions, the microcontroller 112 acquires a resting-state working signal of a preset duration and calculates the average amplitude or root mean square value of the resting-state working signal as the current background noise level. The preset rising edge trigger threshold can be set to the background noise level plus a first safety margin, and the preset falling edge termination threshold can be set to the background noise level plus a second safety margin. In this way, the sensing component 110 can automatically adapt to the individual differences of different users, ensuring that there are no missed detections when the signal is weak and no false detections when the noise is high.

[0043] Optionally, the preset rising edge trigger threshold and the preset falling edge end threshold can also be dynamically determined based on the user's resting uterine electromyography (EMG) signal. Specifically, the microcontroller 112 acquires resting uterine EMG signals of a preset duration during the initial stage of device startup and / or the interval between two uterine contractions, calculates the average amplitude, root mean square (RMS) value, and / or background noise level of the resting uterine EMG signal, and determines the individual baseline based on the average amplitude, RMS value, and / or background noise level; the preset rising edge trigger threshold and the preset falling edge end threshold are dynamically determined based on the individual baseline and the preset safety margin.

[0044] For example, the preset rising edge trigger threshold can be set to the individual baseline plus a first safety margin, and the preset falling edge end threshold can be set to the individual baseline plus a second safety margin, wherein the first safety margin is greater than or equal to the second safety margin.

[0045] By setting preset rising edge trigger thresholds and preset falling edge end thresholds, false triggers caused by minor signal fluctuations can be effectively avoided, ensuring the accuracy of contraction recognition. For example, when the amplitude of the contraction waveform envelope curve crosses the preset rising edge trigger threshold from bottom to top, the contraction is determined to have started, and the current time is recorded as the start time; conversely, when the amplitude of the contraction waveform envelope curve crosses the preset falling edge end threshold from top to bottom, the contraction is determined to have ended, and the current time is recorded as the end time.

[0046] After obtaining the end time and the start time, calculate the time difference between the end time and the start time. This time difference is the duration of the burst wave of this contraction. Within the time window formed by the start time and the end time, traverse the envelope curve of the contraction waveform, extract the maximum amplitude, and take this maximum value as the peak intensity of the current contraction.

[0047] The microcontroller 112 determines the final operating parameters based on the calculated duration of the burst wave, peak intensity, rising slope or growth rate of the uterine contraction waveform envelope curve, peak duration, falling slope or falling rate, contraction interval, and / or contraction density per unit time. In other words, the operating parameters can be data including one or more of intensity, duration, trend of change, and contraction rhythm, used to identify the current state of uterine electromyographic activity and its transition trend.

[0048] In other embodiments, the microcontroller 112 may also be a comprehensive intensity score calculated according to a preset scoring formula, and the comprehensive intensity score may be determined as an operating parameter. The preset scoring formula may include one or more of peak intensity, duration, upward trend weight, peak maintenance weight, downward trend weight, and / or uterine contraction rhythm weight; for example, the operating parameter may include a product term of peak intensity and duration. It is understood that this application is not limited to limiting the specific expression of the preset scoring formula.

[0049] In one specific implementation, the control component 120 can be a back-mounted host, which is configured to be worn on the user's back, receiving wireless data from the sensing component 110 and outputting a target electrical stimulation signal based on the wireless data.

[0050] The control component 120 may include a control chip, a single-channel dual-output electrical stimulation module, and a wireless communication module 113. The control component 120 is connected to the first stimulation electrode 130 and the second stimulation electrode 140 via physical interfaces such as a magnetic interface or a Type-C interface. The control chip may be an MCU. The control component 120 establishes a wireless communication connection with the sensing component 110 via the wireless communication module 113 to receive the operating parameters transmitted by the sensing component 110 in real time.

[0051] The Type-C interface is configured as a multiplexed interface, used both for wired electrical connection with the first stimulation electrode 130 or the second stimulation electrode 140 to output a target electrical stimulation signal, and for connecting to an external charging power source to charge the battery inside the control component 120. The magnetic interface is configured to quickly connect to the first stimulation electrode 130 or the second stimulation electrode 140 via magnetic attraction, enabling rapid connection of the wireless electrodes.

[0052] In some implementations, in order to simplify the initial configuration process of the electrostimulation system 100, when the sensing component 110 is triggered and started by the power button, the wireless communication module 113 will automatically enter the scanning and connection state and actively establish a wireless communication link with the control component 120, so as to realize plug-and-play after the electrostimulation system 100 is started, thereby significantly shortening the preparation time of the electrostimulation system 100.

[0053] Specifically, in some embodiments, the control component 120 is configured to: when the uterine electromyographic activity state is at least one of the following: intercontraction state, precontraction migration state, contraction regression state, or contraction recovery state, or when the state migration trend indicates that contraction has not started, contraction is weakening, or contraction has ended, operate a first working mode to cause the first stimulation electrode and the second stimulation electrode to output a first target electrical stimulation signal; the first target electrical stimulation signal is at least one of the following: a basic analgesia signal, a low-intensity maintenance signal, or a recovery stimulation signal.

[0054] The intercontraction interval can be a relatively resting physiological phase between two contraction bursts. The pre-contraction migration phase can be the initial stage during a contraction cycle where uterine electromyographic activity begins to increase but has not yet reached the high-intensity contraction. The contraction regression phase can be the physiological phase during a contraction burst cycle where uterine electromyographic activity begins to decline after exceeding its peak. The contraction recovery phase can be the stage where a single contraction burst completely ends and uterine electromyographic activity returns to its resting baseline.

[0055] In some embodiments, the control component 120 is further configured to: when the uterine electromyographic activity state is at least one of an enhanced uterine contraction state or a peak uterine contraction state, or when the state transition trend indicates enhanced uterine contraction or increased pain stimulation demand, operate a second working mode to cause the first stimulation electrode and the second stimulation electrode to output a second target electrical stimulation signal; the frequency, pulse width and / or output intensity of the second target electrical stimulation signal are higher than or different from the first target electrical stimulation signal, and are dynamically determined according to the working parameters.

[0056] The enhanced contraction state can be defined as the physiological phase in which uterine electrical activity rapidly increases after the initial initiation phase during a contraction burst cycle. The peak contraction state can be defined as the phase in which uterine electrical activity reaches its highest intensity during the current cycle.

[0057] The current state of uterine electromyography and its state transition trend can be determined by state identification conditions. In other words, the state identification conditions can be the logical judgment basis or rule set used by the control component 120 to identify the current state of uterine electromyography and its state transition trend.

[0058] Optionally, the state identification conditions may include preset empirical identification conditions, individual baseline identification conditions, and / or dynamic identification conditions. Preset empirical identification conditions may be reference conditions obtained during the development phase of the electrical stimulation system 100 based on statistical analysis of uterine electromyography (EMG) signal data from clinical users, and pre-stored in the memory of the control component 120. Individual baseline identification conditions can be determined based on resting-state EMG signals collected from the current user during the initial device startup and / or uterine contraction intervals. Dynamic identification conditions can be dynamically updated based on the changing trends of real-time operating parameters relative to the individual baseline, uterine contraction density, and / or the average value of uterine EMG signals within the most recent preset time window.

[0059] Optionally, to accommodate differences in pain tolerance, skin impedance, and labor progress among users, the control component 120 is configured to allow users to manually adjust the stimulation output intensity or comfort level. Users can manually increase or decrease the output intensity, frequency level, pulse width level, and / or mode level of the target electrical stimulation signal via a wireless remote control component. Upon receiving a manual adjustment command, the control component 120 modifies the target electrical stimulation strategy within a safe output range; however, manual adjustment does not alter the fundamental logic of automatic identification and closed-loop control based on the state of uterine myoelectric activity and its transition trends.

[0060] In other embodiments, the control component 120 can preset multiple state identification conditions, which are used to distinguish different states of uterine electromyography (UEM) activity and the migration trend between adjacent states. For example, the control component 120 can determine the current state of uterine EMM activity based on whether real-time operating parameters meet the identification conditions corresponding to the state before contraction migration, the first contraction activity state, the second contraction activity state, the strengthening state, or the recovery state. When the operating parameters continuously meet the corresponding state identification conditions for a preset confirmation time, the control component 120 confirms that a state migration has occurred and adjusts the frequency, pulse width, and / or output intensity of the target electrical stimulation signal according to the migrated uterine EMM activity state. Thus, multiple state identification conditions are used to achieve state migration recognition and smooth switching of stimulation strategies, rather than simply increasing the target pulse width or stimulation frequency in a stepwise manner according to a fixed threshold.

[0061] In one specific implementation, when the uterine myoelectric activity is in the pre-contraction migration state or the inter-contraction period state, the control component 120 controls the single-channel dual-output electrical stimulation module to output a first basic electrical stimulation signal. The frequency range of the first basic electrical stimulation signal is 1-15Hz, the pulse width range is 120-250μs, and the current range is 5-20mA, which is used for continuous relaxation and analgesia and to avoid strong stimulation during the analgesia period. When the uterine myoelectric activity is in the first uterine contraction activity state or the uterine contraction intensity is weak and shows an increasing trend, the control component 120 controls the single-channel dual-output electrical stimulation module to output a second basic electrical stimulation signal. The frequency range of the second basic electrical stimulation signal is 50-100Hz, the pulse width range is 100-220μs, and the current range is 10-35mA.

[0062] Optionally, when the real-time RMS continuous preset time exceeds a preset multiple of the individual baseline and the RMS growth rate reaches a preset growth condition, the control component smoothly transitions the frequency, pulse width and / or current from the first basic electrical stimulation signal to the second basic electrical stimulation signal within 0.3 to 0.8 seconds.

[0063] When the uterine electromyographic activity state is in the second uterine contraction activity state, the enhanced state, or the state transition trend indicates increased uterine contraction, maintenance of uterine contraction peak, or increased demand for pain stimulation, the control component 120 controls the single-channel dual-output electrical stimulation module to run an enhanced output strategy. Under the enhanced output strategy, the frequency, pulse width, and / or output intensity of the target electrical stimulation signal output by the first stimulation electrode 130 and the second stimulation electrode 140 are dynamically determined according to the current uterine electromyographic activity state, the stage of a single uterine contraction, and the operating parameters.

[0064] Optionally, the target electrical stimulation signal frequency range for the enhanced phase of the second uterine contraction activity is 80–130 Hz, the pulse width range is 180–280 μs, and the current range is 20–50 mA; the target electrical stimulation signal frequency range for the peak phase of the second uterine contraction activity is 100–150 Hz, the pulse width range is 200–300 μs, and the current range is 25–60 mA; and the target electrical stimulation signal frequency range for the enhanced activity phase is 120–180 Hz and can be extended to 200 Hz, the pulse width range is 220–300 μs, and the current range is 30–60 mA.

[0065] The parameters of the target electrical stimulation signal are not fixed values, but are dynamically determined within a preset range based on the identified state of uterine electromyography, the stage of a single uterine contraction, the state transition trend, and / or the working parameters. The parameters include at least one of frequency, pulse width, and / or output intensity.

[0066] Optionally, the control component 120 performs interpolation calculations based on the ratio of the current operating parameters to the corresponding state parameter boundary, within the frequency range, pulse width range, and current range corresponding to the state; when the state transition trend indicates increased uterine contractions, the stimulation parameter level is increased; when the state transition trend indicates decreased or recovered uterine contractions, the stimulation parameter level is decreased or a recovery output strategy is entered.

[0067] For example, when the control component 120 detects that the uterine electromyographic activity state has shifted from the pre-contraction state to the first contraction state, the control component 120 smoothly transitions the target electrical stimulation signal from the first basic electrical stimulation signal to the second basic electrical stimulation signal within a preset transition time; when the control component 120 detects that the uterine electromyographic activity state has shifted from the first contraction state to the second contraction state or the enhanced state, the control component 120 increases the frequency, pulse width, and / or output intensity of the target electrical stimulation signal within the parameter range of the corresponding state; when the control component 120 detects that the contraction has subsided or recovered, the control component 120 decreases the frequency, pulse width, and / or output intensity of the target electrical stimulation signal, or enters a recovery output strategy.

[0068] Furthermore, in some embodiments, the control component 120 is also configured to: monitor the connection status with the first stimulation electrode 130 and the second stimulation electrode 140; when it is detected that both the first stimulation electrode 130 and the second stimulation electrode 140 are in a connected state, control the first stimulation electrode 130 and the second stimulation electrode 140 to synchronously output the target electrical stimulation signal; when it is detected that either the first stimulation electrode 130 or the second stimulation electrode 140 is in a disconnected state, control the first stimulation electrode 130 and the second stimulation electrode 140 to synchronously stop outputting the target electrical stimulation signal.

[0069] The control component 120 is configured to monitor the connection status with the first stimulation electrode 130 and the second stimulation electrode 140 in real time before or during the output of the target electrical stimulation signal. For example, the control component 120 sends a weak detection current to the first stimulation electrode 130 and the second stimulation electrode 140 and measures their loop impedance. When the loop impedance is within a preset normal human body impedance range, the electrode is determined to be in a valid connection state; when the loop impedance exceeds the preset normal human body impedance range or is open, the electrode is determined to be in a disconnected state.

[0070] When the control component 120 detects that both the first stimulation electrode 130 and the second stimulation electrode 140 are connected, it indicates that the analgesia circuits of the T10-L1 segment and the S2-S4 segment of the back have been established. The control component 120 releases the safety lock, controls the single-channel dual-output electrical stimulation module to work normally, and drives the first stimulation electrode 130 and the second stimulation electrode 140 to output the target electrical stimulation signal synchronously to achieve coordinated analgesia of the two targets.

[0071] When the control component 120 detects that the first stimulation electrode 130 or the second stimulation electrode 140 is in a disconnected state, the control component 120 immediately controls the single-channel dual-output electrical stimulation module to stop working, so that the first stimulation electrode 130 and the second stimulation electrode 140 simultaneously stop outputting the target electrical stimulation signal.

[0072] Only when both the first stimulation electrode 130 and the second stimulation electrode 140 are detected to be connected will the first stimulation electrode 130 and the second stimulation electrode 140 be controlled to output the target electrical stimulation signal synchronously. When either stimulation electrode is detached, open-circuited, or has abnormal impedance, the output will stop synchronously to avoid abnormal stimulation in a single circuit and improve safety.

[0073] As can be seen from the above description, in order to adapt to individual needs, some implementation methods may vary. Please refer to [link / reference needed]. Figure 3 , Figure 3 A schematic diagram of another electrical stimulation system 100 according to an embodiment of this application is shown, as follows. Figure 3 As shown, the electrical stimulation system 100 also includes a wireless remote control component 150, which is wirelessly connected to the control component 120.

[0074] The wireless remote control component 150 is configured to receive a manual adjustment command and send the manual adjustment command to the control component 120; the manual adjustment command includes at least one of a mode switching command, an intensity adjustment command, or a start / stop control command; the control component 120 is also configured to adjust the target electrical stimulation signal output by the first stimulation electrode 130 and the second stimulation electrode 140 in response to the manual adjustment command.

[0075] The wireless remote control component 150 establishes a wireless communication connection with the control component 120, for example, based on Bluetooth, Wi-Fi, or a proprietary 2.4G wireless protocol. The wireless remote control component 150 can be a standalone handheld remote control or a smart terminal with a dedicated control app installed, such as a smartphone or tablet.

[0076] The wireless remote control component 150 is configured as an entry point for human-computer interaction, used to receive manual adjustment commands from the user and convert the manual adjustment commands into wireless signals to be sent to the control component 120.

[0077] In embodiments of this application, the mode switching command is used to switch between a first operating mode and a second operating mode. The intensity adjustment command is used to fine-tune the amplitude, pulse width, or frequency of the target electrical stimulation signal within the safe range allowed by the electrical stimulation system 100 to match the user's real-time situation. The start / stop control command is used to urgently pause or restart the output of the target electrical stimulation signal.

[0078] Please see Figure 4 , Figure 4 A schematic flowchart of an electrical stimulation method provided in an embodiment of this application is shown, as follows: Figure 4 As shown, the method may include steps 210 to 230.

[0079] In step 210, working signals characterizing changes in the state of uterine myoelectric activity are acquired.

[0080] In some implementations, the working signal can be a raw electrical signal collected by the sensing component that reflects the physiological activity of uterine contractions. The working signal can be a uterine electromyographic signal. When the user experiences uterine contractions, the uterine smooth muscle generates electrophysiological activity. The sensing component, through its internal differential electromyographic electrodes, is attached to the mother's abdomen to collect the weak electrical signal generated by this physiological activity and uses it as the working signal.

[0081] In step 220, the working signal is analyzed to generate working parameters that characterize the current uterine contraction activity status and trend.

[0082] In some implementations, the operating parameters may be multidimensional data including burst wave duration, peak intensity, signal change trend, and / or uterine contraction rhythm information per unit time; wherein the signal change trend is used to characterize at least one state change among uterine contraction enhancement, peak maintenance, uterine contraction decline, or recovery.

[0083] After acquiring the working signal, the sensing component further performs feature analysis processing such as filtering, amplification, and envelope extraction, thereby transforming the original analog working signal into digital working parameters that can accurately characterize the current uterine contraction activity status and changing trend.

[0084] Specifically, in some implementations, performing feature analysis on the working signals to generate working parameters characterizing the current state and trend of uterine contractions may further include the following steps: (1) Filter and amplify the working signal to obtain the processed working signal; (2) Extract the envelope of the processed working signal to obtain the uterine contraction waveform envelope curve; (3) Based on the preset rising edge trigger threshold and the preset falling edge end threshold, the state of the uterine contraction waveform envelope curve is determined to determine the start and end times of the current uterine contraction; (4) The duration of the burst wave is obtained based on the time difference between the start and end times; (5) Within the time window between the start and end times, extract the maximum amplitude of the uterine contraction waveform envelope curve and use it as the peak intensity of the current uterine contraction. (6) Determine the working parameters based on the duration of the burst wave, peak intensity, signal change trend and / or uterine contraction rhythm information per unit time; wherein, the signal change trend includes parameters characterizing the enhancement, peak maintenance or decline of uterine electromyography signal, and the uterine contraction rhythm information per unit time includes uterine contraction interval and / or uterine contraction density.

[0085] The acquired working signal is filtered and amplified. A bandpass filter removes power frequency interference and baseline drift noise, and weak signals are amplified to obtain a processed working signal with a signal-to-noise ratio that meets processing requirements. Envelope extraction is performed on the processed working signal to reconstruct the uterine contraction waveform envelope curve, which intuitively reflects the trend of uterine contraction energy changes. After determining the start and end times, the duration of the burst wave, peak intensity, rising trend, peak maintenance state, and falling trend can be extracted within this time window. These parameters can be combined with the time interval between adjacent contractions or the contraction density per unit time to form working parameters for state transition judgment.

[0086] In step 230, the current state of uterine myoelectric activity and its state transition trend are identified according to the working parameters, and the target electrical stimulation strategy is determined based on the state of uterine myoelectric activity and its state transition trend. The target electrical stimulation signal is generated and the first stimulation electrode and the second stimulation electrode are driven by a single channel to output the target electrical stimulation signal synchronously.

[0087] The target electrical stimulation signal can be an electrical pulse control signal used by the control component to directly drive the first and second stimulation electrodes based on the comparison results of the operating parameters and preset thresholds.

[0088] When the uterine myoelectric activity is in the pre-contraction migration state or the inter-contraction period state, the target electrical stimulation signal is specifically manifested as the first basic electrical stimulation signal, with a frequency range of 1-15Hz, a pulse width range of 120-250μs, and a current range of 5-20mA. When the uterine myoelectric activity is in the first uterine contraction state or the uterine contraction intensity is weak and shows an increasing trend, the target electrical stimulation signal is specifically manifested as the second basic electrical stimulation signal, with a frequency range of 50-100Hz, a pulse width range of 100-220μs, and a current range of 10-35mA.

[0089] When the uterine electromyography (EMG) activity is in the second contraction activity state, the enhanced state, or the state transition trend indicates that the contraction is strengthening or the peak is maintained, the frequency, pulse width, and / or output intensity of the target electrical stimulation signal are dynamically determined according to the current uterine EMG activity state, the stage of a single contraction, and the working parameters; when the uterine EMG activity is in the contraction decline state or the recovery state, the frequency, pulse width, and / or output intensity of the target electrical stimulation signal are reduced, or a mild recovery, moderate recovery, or deep recovery output strategy is entered.

[0090] In some embodiments, the electrical stimulation method may further include the following steps: (1) Monitor the connection status of the first stimulation electrode and the second stimulation electrode; (2) When it is detected that both the first stimulation electrode and the second stimulation electrode are in a connected state, control the first stimulation electrode and the second stimulation electrode to output the target electrical stimulation signal synchronously; (3) When the first stimulation electrode or the second stimulation electrode is detected to be in the off state, the first stimulation electrode and the second stimulation electrode are controlled to stop outputting the target electrical stimulation signal synchronously.

[0091] The control component connects to the first and second stimulation electrodes via physical interfaces such as a magnetic connector or a Type-C interface. The control chip can be an MCU, and the control component establishes a wireless communication connection with the sensing component via a wireless communication module to receive its operating parameters in real time.

[0092] The Type-C interface is configured as a multiplexed interface, used both for wired connection to the first or second stimulating electrode to output the target electrical stimulation signal, and for connecting to an external charging power source to charge the battery inside the control component. The magnetic interface is configured to quickly connect to the first or second stimulating electrode via magnetic attraction, enabling rapid connection of the wireless electrode.

[0093] In some implementations, to simplify the initial configuration process of the electrical stimulation system, when the sensing component is triggered by the power button, the wireless communication module will automatically enter the scanning and connection state and actively establish a wireless communication link with the control component, so as to realize plug-and-play after the electrical stimulation system is started, thereby significantly shortening the preparation time of the electrical stimulation system.

[0094] Specifically, in some embodiments, the control component is configured to: when the operating parameters are less than a preset threshold, operate a first operating mode to make the first stimulating electrode and the second stimulating electrode output continuous pulse signals with a preset frequency; when the operating parameters are greater than or equal to the preset threshold, operate a second operating mode to make the first stimulating electrode and the second stimulating electrode output target electrical stimulation signals with a target pulse width, wherein the target pulse width is determined according to the value of the operating parameters.

[0095] Optionally, the status identification conditions may include preset empirical identification conditions, individual baseline identification conditions, and / or dynamic identification conditions. Preset empirical identification conditions may be reference conditions obtained during the development phase of the electrical stimulation system based on statistical analysis of uterine electromyography (EMG) signal data from clinical users, and pre-stored in the memory of the control component. Individual baseline identification conditions can be determined based on resting-state EMG signals collected from the current user during the initial device startup and / or uterine contraction intervals. Dynamic identification conditions can be dynamically updated based on the changing trends of real-time operating parameters relative to the individual baseline, uterine contraction density, and / or the average value of uterine EMG signals within the most recent preset time window.

[0096] Optionally, to accommodate differences in pain tolerance, skin impedance, and labor progress among users, the control component is configured to allow users to manually adjust the stimulation output intensity or comfort level. Users can manually increase or decrease the output intensity, frequency level, pulse width level, and / or mode level of the target electrical stimulation signal via a wireless remote control component. Upon receiving a manual adjustment command, the control component corrects the target electrical stimulation strategy within a safe output range, but manual adjustment does not alter the fundamental logic of automatic identification and closed-loop control based on the state of uterine myoelectric activity and its state transition trends.

[0097] In other embodiments, the control component can preset multiple state identification conditions. These conditions are used to distinguish different states of uterine electromyography (EMG) activity and the migration trends between adjacent states. For example, the control component determines the current state of uterine EMG activity based on whether real-time operating parameters meet the identification conditions corresponding to the state before contraction migration, the first contraction activity state, the second contraction activity state, the strengthening state, or the recovery state. When the operating parameters continuously meet the corresponding state identification conditions for a preset confirmation time, the control component confirms that a state migration has occurred and adjusts the frequency, pulse width, and / or output intensity of the target electrical stimulation signal according to the migrated uterine EMG activity state. Thus, multiple state identification conditions are used to achieve state migration recognition and smooth switching of stimulation strategies, rather than simply increasing the target pulse width or stimulation frequency in a stepwise manner according to a fixed threshold.

[0098] When the uterine electromyography activity is in the pre-contraction migration state or the inter-contraction state, the control component controls the single-channel dual-output electrical stimulation module to output the first basic electrical stimulation signal. The frequency range of the first basic electrical stimulation signal is 1-15Hz, the pulse width range is 120-250μs, and the current range is 5-20mA, which is used for continuous relaxation and analgesia and to avoid strong stimulation during the painless period. When the uterine electromyographic activity is in the first uterine contraction state or the contraction intensity is weak but showing an increasing trend, the control component controls the single-channel dual-output electrical stimulation module to output a second basic electrical stimulation signal. The frequency range of the second basic electrical stimulation signal is 50-100Hz, the pulse width range is 100-220μs, and the current range is 10-35mA. Optionally, when the real-time RMS continuous preset time is detected to exceed a preset multiple of the individual baseline and the RMS growth rate reaches a preset growth condition, the control component smoothly transitions the frequency, pulse width, and / or current from the first basic electrical stimulation signal to the second basic electrical stimulation signal within 0.3-0.8 seconds.

[0099] The parameters of the target electrical stimulation signal are not fixed values, but are dynamically determined within a preset range based on the identified state of uterine electromyography, the stage of a single uterine contraction, the state transition trend, and / or the operating parameters. The parameters include at least one of frequency, pulse width, and / or output intensity. Optionally, the control component 120 performs interpolation calculations within the frequency range, pulse width range, and current range corresponding to the state, based on the ratio of the current operating parameters to the boundary of the corresponding state parameters; when the state transition trend indicates increased uterine contractions, the stimulation parameter level is increased; when the state transition trend indicates decreased or recovered uterine contractions, the stimulation parameter level is decreased or a recovery output strategy is entered.

[0100] For example, when the control component detects that the uterine electromyographic activity state has shifted from the pre-contraction state to the first contraction state, the control component smoothly transitions the target electrical stimulation signal from the first baseline electrical stimulation signal to the second baseline electrical stimulation signal within a preset transition time; when the control component detects that the uterine electromyographic activity state has shifted from the first contraction state to the second contraction state or the enhanced state, the control component increases the frequency, pulse width, and / or output intensity of the target electrical stimulation signal within the parameter range of the corresponding state; when the control component detects that the contraction has subsided or recovered, the control component decreases the frequency, pulse width, and / or output intensity of the target electrical stimulation signal, or enters a recovery output strategy.

[0101] Furthermore, in some embodiments, the control component is also configured to: monitor the connection status with the first stimulation electrode and the second stimulation electrode; when both the first stimulation electrode and the second stimulation electrode are detected to be connected, control the first stimulation electrode and the second stimulation electrode to synchronously output the target electrical stimulation signal; when either the first stimulation electrode or the second stimulation electrode is detected to be disconnected, control the first stimulation electrode and the second stimulation electrode to synchronously stop outputting the target electrical stimulation signal.

[0102] The control component is configured to monitor the connection status of the first and second stimulation electrodes in real time before or during the output of the target electrical stimulation signal. For example, the control component sends a weak detection current to the first and second stimulation electrodes and measures their loop impedance. When the loop impedance is within a preset range of normal human body impedance, the electrodes are determined to be in a valid connection state; when the loop impedance exceeds the preset range of normal human body impedance or is open-circuited, the electrodes are determined to be in a disconnected state.

[0103] When the control component detects that both the first and second stimulation electrodes are connected, it indicates that the analgesic circuits of the T10-L1 and S2-S4 segments of the back have been established. The control component releases the safety lock and controls the single-channel dual-output electrical stimulation module to work normally, driving the first and second stimulation electrodes to synchronously output target electrical stimulation signals to achieve coordinated analgesia at two targets.

[0104] When the control component detects that the first or second stimulation electrode is disconnected, the control component immediately controls the single-channel dual-output electrical stimulation module to stop working, so that the first and second stimulation electrodes synchronously stop outputting the target electrical stimulation signal.

[0105] Only when both the first and second stimulation electrodes are detected to be connected can the first and second stimulation electrodes be controlled to output the target electrical stimulation signal synchronously, thus avoiding uneven analgesic effects caused by unilateral detachment.

[0106] The control component connects to the first and second stimulation electrodes via physical interfaces such as a magnetic connector or a Type-C interface. The control chip can be an MCU, and the control component establishes a wireless communication connection with the sensing component via a wireless communication module to receive its operating parameters in real time.

[0107] The Type-C interface is configured as a multiplexed interface, used both for wired connection to the first or second stimulating electrode to output the target electrical stimulation signal, and for connecting to an external charging power source to charge the battery inside the control component. The magnetic interface is configured to quickly connect to the first or second stimulating electrode via magnetic attraction, enabling rapid connection of the wireless electrode.

[0108] In some implementations, to simplify the initial configuration process of the electrical stimulation system, when the sensing component is triggered by the power button, the wireless communication module will automatically enter the scanning and connection state and actively establish a wireless communication link with the control component, so as to realize plug-and-play after the electrical stimulation system is started, thereby significantly shortening the preparation time of the electrical stimulation system.

[0109] Specifically, in some embodiments, the control component is configured to: when the operating parameters are less than a preset threshold, operate a first operating mode to make the first stimulating electrode and the second stimulating electrode output continuous pulse signals with a preset frequency; when the operating parameters are greater than or equal to the preset threshold, operate a second operating mode to make the first stimulating electrode and the second stimulating electrode output target electrical stimulation signals with a target pulse width, wherein the target pulse width is determined according to the value of the operating parameters.

[0110] Optionally, the preset threshold can be an empirical value derived from statistical analysis of uterine electromyography signal data from a large number of clinical users during the development phase of the electrical stimulation system, and can be pre-fixed and stored in the memory of the control component.

[0111] Optionally, to accommodate differences in pain tolerance and skin impedance among users, the control component is configured to support customizable thresholds. Users can manually adjust preset thresholds up or down via a wireless remote control component (described in detail later) to achieve a personalized analgesia experience.

[0112] In other implementations, the control component may also have multiple preset thresholds arranged in a stepped manner, such as a first threshold, a second threshold, etc. When the operating parameters reach different threshold levels, the control component can generate target electrical stimulation signals of different intensities, for example, by stepwise increasing the target pulse width or stimulation frequency, thereby achieving more refined multi-level analgesia control.

[0113] When the uterine myoelectric activity is in the pre-contraction migration state or the inter-contraction period state, the control component controls the single-channel dual-output electrical stimulation module to output the first basic electrical stimulation signal. The frequency range of the first basic electrical stimulation signal is 1-15Hz, the pulse width range is 120-250μs, and the current range is 5-20mA. This signal is used for continuous relaxation and analgesia and to avoid strong stimulation during the analgesia period. When the uterine myoelectric activity is in the first uterine contraction activity state or the uterine contraction intensity is weak and shows an increasing trend, the control component controls the single-channel dual-output electrical stimulation module to output the second basic electrical stimulation signal. The frequency range of the second basic electrical stimulation signal is 50-100Hz, the pulse width range is 100-220μs, and the current range is 10-35mA.

[0114] Optionally, when the real-time RMS continuous preset time exceeds a preset multiple of the individual baseline and the RMS growth rate reaches a preset growth condition, the control component smoothly transitions the frequency, pulse width and / or current from the first basic electrical stimulation signal to the second basic electrical stimulation signal within 0.3 to 0.8 seconds.

[0115] The parameters of the target electrical stimulation signal are not fixed values, but are dynamically determined within a preset range based on the identified state of uterine electromyography, the stage of a single uterine contraction, the state transition trend, and / or the operating parameters. The parameters include at least one of frequency, pulse width, and / or output intensity. Optionally, the control component performs interpolation calculations within the frequency range, pulse width range, and current range corresponding to the state, based on the ratio of the current operating parameters to the boundary of the corresponding state parameters; when the state transition trend indicates increased uterine contractions, the stimulation parameter level is increased; when the state transition trend indicates decreased or recovered uterine contractions, the stimulation parameter level is decreased or a recovery output strategy is entered.

[0116] For example, when the control component detects that the uterine electromyographic activity state has shifted from the pre-contraction state to the first contraction state, the control component smoothly transitions the target electrical stimulation signal from the first baseline electrical stimulation signal to the second baseline electrical stimulation signal within a preset transition time; when the control component detects that the uterine electromyographic activity state has shifted from the first contraction state to the second contraction state or the enhanced state, the control component increases the frequency, pulse width, and / or output intensity of the target electrical stimulation signal within the parameter range of the corresponding state; when the control component detects that the contraction has subsided or recovered, the control component decreases the frequency, pulse width, and / or output intensity of the target electrical stimulation signal, or enters a recovery output strategy.

[0117] Furthermore, in some embodiments, the control component is also configured to: monitor the connection status with the first stimulation electrode and the second stimulation electrode; when both the first stimulation electrode and the second stimulation electrode are detected to be connected, control the first stimulation electrode and the second stimulation electrode to synchronously output the target electrical stimulation signal; when either the first stimulation electrode or the second stimulation electrode is detected to be disconnected, control the first stimulation electrode and the second stimulation electrode to synchronously stop outputting the target electrical stimulation signal.

[0118] The control component is configured to monitor the connection status of the first and second stimulation electrodes in real time before or during the output of the target electrical stimulation signal. For example, the control component sends a weak detection current to the first and second stimulation electrodes and measures their loop impedance. When the loop impedance is within a preset range of normal human body impedance, the electrodes are determined to be in a valid connection state; when the loop impedance exceeds the preset range of normal human body impedance or is open-circuited, the electrodes are determined to be in a disconnected state.

[0119] When the control component detects that both the first and second stimulation electrodes are connected, it indicates that the analgesic circuits of the T10-L1 and S2-S4 segments of the back have been established. The control component releases the safety lock and controls the single-channel dual-output electrical stimulation module to work normally, driving the first and second stimulation electrodes to synchronously output target electrical stimulation signals to achieve coordinated analgesia at two targets.

[0120] When the control component detects that the first or second stimulation electrode is disconnected, the control component immediately controls the single-channel dual-output electrical stimulation module to stop working, so that the first and second stimulation electrodes synchronously stop outputting the target electrical stimulation signal.

[0121] Only when both the first and second stimulating electrodes are detected to be connected can the first and second stimulating electrodes be controlled to output the target electrical stimulation signal synchronously, thus avoiding uneven analgesic effects caused by unilateral detachment.

[0122] Please see Figure 5 , Figure 5 The diagram illustrates the structure of an electronic device according to an embodiment of this application. The electronic device 300 in this application may include one or more of the following components: a processor 310, a memory 320, and one or more application programs. The one or more application programs may be stored in the memory 320 and configured to be executed by one or more processors 310. The one or more programs are configured to perform the electrical stimulation method as described in the foregoing method embodiments.

[0123] Processor 310 may include one or more processing cores. Processor 310 connects to various parts within the electronic device 300 using various interfaces and lines, and performs various functions and processes data of the electronic device 300 by running or executing instructions, programs, code sets, or instruction sets stored in memory 320, and by calling data stored in memory 320. Optionally, processor 310 may be implemented using at least one hardware form of Digital Signal Processing (DSP), Field-Programmable Gate Array (FPGA), or Programmable Logic Array (PLA). Processor 310 may integrate one or a combination of several of the following: Central Processing Unit (CPU), Graphics Processing Unit (GPU), and modem. The CPU primarily handles the operating system, user interface, and applications; the GPU is responsible for rendering and drawing the displayed content; and the modem handles wireless communication. It is understood that the modem may also not be integrated into processor 310 and may be implemented separately using a communication chip.

[0124] The memory 320 may include random access memory (RAM) or read-only memory (ROM). The memory 320 can be used to store instructions, programs, code, code sets, or instruction sets. The memory 320 may include a program storage area and a data storage area. The program storage area may store instructions for implementing an operating system, instructions for implementing at least one function, instructions for implementing the various method embodiments described below, etc. The data storage area may also store data created by the electronic device 300 during use.

[0125] Please see Figure 6 , Figure 6 The diagram shows a computer-readable storage medium 400 provided in an embodiment of this application. The computer-readable storage medium 400 stores program code, which can be called by a processor to execute the electrical stimulation method described in the above method embodiment.

[0126] The computer-readable storage medium 400 may be an electronic memory such as flash memory, EEPROM (Electrically Erasable Programmable Read-Only Memory), EPROM, hard disk, or ROM. Optionally, the computer-readable storage medium 400 includes a non-transitory computer-readable storage medium. The computer-readable storage medium 400 has storage space for program code 410 that performs any of the method steps described above. This program code can be read from or written to one or more computer program devices. The program code 410 may be compressed, for example, in a suitable form.

[0127] Finally, it should be noted that the above embodiments are only used to illustrate the technical solutions of this application, and are not intended to limit them. Although this application has been described in detail with reference to the foregoing embodiments, those skilled in the art should understand that modifications can still be made to the technical solutions described in the foregoing embodiments, or equivalent substitutions can be made to some of the technical features. Such modifications or substitutions do not cause the essence of the corresponding technical solutions to deviate from the spirit and scope of the technical solutions of the embodiments of this application.

Claims

1. An electrical stimulation system, characterized in that, include: The sensing component is configured to acquire working signals that characterize changes in the state of uterine electromyographic activity, and to perform feature analysis on the working signals to generate working parameters that characterize the current state and trend of uterine contraction activity. The control component is wirelessly connected to the sensing component; The first and second stimulation electrodes are respectively connected to the control component; The control component is configured to identify the current state of uterine electromyography and its state transition trend based on the operating parameters, determine the target electrical stimulation strategy based on the state of uterine electromyography and its state transition trend, generate the target electrical stimulation signal, and synchronously output the target electrical stimulation signal by driving the first stimulation electrode and the second stimulation electrode through a single channel.

2. The electrical stimulation system according to claim 1, characterized in that, The sensing component includes differential electromyography electrodes, a microcontroller, and a wireless communication module, wherein: The differential electromyography electrode is configured to acquire the working signal; The microcontroller is configured to perform feature analysis on the operating signal to generate the operating parameters; A wireless communication module, wirelessly connected to the control component, is configured to send the operating parameters to the control component.

3. The electrical stimulation system according to claim 1, characterized in that, The sensing component is configured as follows: The working signal is filtered and amplified to obtain the processed working signal; The processed working signal is subjected to envelope extraction to obtain the uterine contraction waveform envelope curve; Based on a preset rising edge trigger threshold and a preset falling edge end threshold, the state of the uterine contraction waveform envelope curve is determined to identify the start and end times. The duration of the burst wave is obtained based on the time difference between the start time and the end time. Within the time window between the start time and the end time, the maximum amplitude of the uterine contraction waveform envelope curve is extracted and used as the peak intensity of the current uterine contraction. The operating parameters are determined based on the duration of the burst wave, the peak intensity, the signal change trend, and / or the uterine contraction rhythm information per unit time; wherein, the signal change trend includes parameters characterizing the enhancement, peak maintenance, or decline of the uterine electromyography signal, and the uterine contraction rhythm information per unit time includes the contraction interval and / or contraction density.

4. The electrical stimulation system according to claim 1, characterized in that, The control component is configured as follows: When the uterine electromyographic activity state is at least one of the following: intercontraction state, precontraction migration state, contraction regression state, or contraction recovery state, or the state migration trend indicates that the contraction has not started, the contraction is weakening, or the contraction has ended, the first working mode is activated so that the first stimulation electrode and the second stimulation electrode output a first target electrical stimulation signal; the first target electrical stimulation signal is at least one of the following: a basic analgesia signal, a low-intensity maintenance signal, or a recovery stimulation signal. When the uterine electromyographic activity state is at least one of enhanced uterine contraction state or peak uterine contraction state, or when the state transition trend indicates enhanced uterine contraction or increased pain stimulation demand, the second working mode is activated so that the first stimulation electrode and the second stimulation electrode output a second target electrical stimulation signal; the frequency, pulse width and / or output intensity of the second target electrical stimulation signal are higher than or different from the first target electrical stimulation signal, and are dynamically determined according to the working parameters.

5. The electrical stimulation system according to claim 1, characterized in that, It also includes a wireless remote control component, which is wirelessly connected to the control component; The wireless remote control component is configured to receive a manual adjustment command and send the manual adjustment command to the control component; the manual adjustment command includes at least one of a mode switching command, an intensity adjustment command, or a start / stop control command. The control component is also configured to adjust the target electrical stimulation signal output by the first stimulation electrode and the second stimulation electrode in response to the manual adjustment command.

6. The electrical stimulation system according to claim 1, characterized in that, The control component is further configured to: Monitor the connection status with the first stimulation electrode and the second stimulation electrode; When it is detected that both the first stimulation electrode and the second stimulation electrode are in a connected state, the first stimulation electrode and the second stimulation electrode are controlled to synchronously output the target electrical stimulation signal. When it is detected that the first stimulation electrode or the second stimulation electrode is in a disconnected state, the first stimulation electrode and the second stimulation electrode are controlled to stop outputting the target electrical stimulation signal synchronously.

7. An electrical stimulation method, characterized in that, include: Acquire working signals characterizing changes in uterine electromyographic activity; The working signal is analyzed for features to generate working parameters that characterize the current uterine contraction activity status and changing trend; The current state of uterine myoelectric activity and its migration trend are identified based on the operating parameters. A target electrical stimulation strategy is determined based on the state of uterine myoelectric activity and its migration trend. A target electrical stimulation signal is generated and the first and second stimulation electrodes are driven by a single channel to output the target electrical stimulation signal synchronously.

8. The electrical stimulation method according to claim 7, characterized in that, The method further includes: Monitor the connection status of the first stimulation electrode and the second stimulation electrode; When it is detected that both the first stimulation electrode and the second stimulation electrode are in a connected state, the first stimulation electrode and the second stimulation electrode are controlled to synchronously output the target electrical stimulation signal. When it is detected that the first stimulation electrode or the second stimulation electrode is in a disconnected state, the first stimulation electrode and the second stimulation electrode are controlled to stop outputting the target electrical stimulation signal synchronously.

9. The electrical stimulation method according to claim 7, characterized in that, The step involves performing feature analysis on the working signal to generate working parameters characterizing the current state and trend of uterine contractions, including: The working signal is filtered and amplified to obtain the processed working signal; The processed working signal is subjected to envelope extraction to obtain the uterine contraction waveform envelope curve; Based on a preset rising edge trigger threshold and a preset falling edge end threshold, the state of the uterine contraction waveform envelope curve is determined to identify the start and end times of the current uterine contraction. The duration of the burst wave is obtained based on the time difference between the start time and the end time. Within the time window between the start time and the end time, the maximum amplitude of the uterine contraction waveform envelope curve is extracted and used as the peak intensity of the current uterine contraction. The operating parameters are determined based on the duration of the burst wave, the peak intensity, the signal change trend, and / or the uterine contraction rhythm information per unit time; wherein, the signal change trend includes parameters characterizing the enhancement, peak maintenance, or decline of the uterine electromyography signal, and the uterine contraction rhythm information per unit time includes the contraction interval and / or contraction density.

10. An electronic device, characterized in that, include: One or more processors; Memory; One or more applications, wherein the one or more applications are stored in the memory and configured to be executed by the one or more processors, the one or more applications being configured to perform the electrical stimulation method as described in any one of claims 7-9.

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