Resistance ladder network-based electric stimulation auxiliary positioning wristband and adjusting method

Abstract

The application discloses a resistance ladder network-based electric stimulation auxiliary positioning wristband and a regulating method. The wristband comprises a host computer, a functional wristband and an electrode module. The functional wristband is internally embedded with mutually insulated conductive conductors. The functional wristband internally embeds the conductive conductors, and is provided with through holes. Adjacent through holes are connected in series with resistors to form a resistance ladder network, so that each through hole is an internal resistance increment access node. The electrode module comprises electrode pieces and conductive columns, which are detachably fixed to the access nodes and electrically connected with the conductors through installation channels. The host computer detects internal resistance increments to identify electrode positions. The method is as follows: impedance decoupling identifies positions, deducts line resistance to obtain net impedance; impedance characteristics identify acupoints; when impedance falls into a nerve interval and presents a minimum value, it is determined that the acupoint is aligned; anatomical characteristics are inferred according to position numbers to call stimulation parameters; skin electric response is closed-loop regulated; charges are discharged before signals are collected in pulse intervals; and parameters are adjusted according to skin electric slopes. The application constructs an intelligent system, and improves electric stimulation accuracy and user experience.

Description

Technical Field

[0001] This invention relates to the field of smart therapeutic wristband technology, and in particular to an electrical stimulation-assisted positioning wristband strap based on a resistive trapezoidal network and its adjustment method. Background Technology

[0002] With the development of internet technology and intelligent products, various intelligent wearable products have emerged on the market. Among them, smart bracelets, as a common type of intelligent wearable product, have brought convenience to users. Existing smart bracelets generally include a watch face and two straps connected to the watch face. The watch face has functions such as monitoring sleep, heart rate, and calorie consumption. The straps are similar to wristbands, with a buckle on one side and a row of small holes on the other side, arranged at intervals. The buckle can be inserted into any of the holes, allowing users to insert the buckle into the most suitable hole according to their wrist size.

[0003] With the widespread application of electrical stimulation therapy in the treatment of diseases such as hypertension, transcutaneous electrical nerve stimulation (TENS) is gradually being integrated into smart bracelets. Low-frequency pulses are transmitted to electrodes on the bracelet via wires embedded within the strap. These electrodes, fixed to the strap, contact the skin to stimulate nerves beneath the skin. However, the length of the strap and the position of the electrodes in traditional smart bracelets are determined by the manufacturer and cannot be changed after manufacturing. Since wrist sizes vary significantly due to individual factors such as height and weight, wearing a traditional strap with fixed length and electrode position on users of different sizes often results in the smart bracelet itself being in the correct position, but the electrode contact point with the skin deviating considerably from the location of the nerve to be stimulated. This significantly reduces the stimulation effect on the target nerve.

[0004] To address the issue of non-adjustable electrode positions, some solutions propose sliding electrode designs, allowing the electrode module to be adjusted on the watch band, enabling users to freely adjust the electrode pads according to their wrist size. However, these solutions only achieve physical adjustment of the electrode's position; the system itself cannot sense the electrode's current location. This means that subsequent stimulation parameter settings still rely on manual input or experience-based judgment by the user, failing to achieve truly intelligent adjustment.

[0005] On the other hand, accurate acquisition of physiological signals is crucial for evaluating treatment efficacy and adjusting parameters during electrostimulation therapy. Current technologies typically use the same electrode or conductive pathway for stimulation and signal acquisition. However, residual charges accumulating on the skin surface after the electrical pulse output can severely interfere with subsequent physiological signal acquisition, leading to distortion of signals such as skin electrical responses and affecting the accuracy of closed-loop regulation. Furthermore, because different electrode positions on the strap correspond to different line lengths and impedances, these line impedances are superimposed on the acquired physiological signals, contaminating the true skin impedance data and causing biases in the assessment of treatment efficacy based on physiological signals.

[0006] Furthermore, the output parameters of existing electrical stimulation therapy devices are usually fixed values ​​based on experience, and cannot be adjusted according to the individual anatomical characteristics of users. Different users have significant differences in wrist circumference, subcutaneous fat thickness, and nerve location depth. Stimulation modes with fixed parameters often cause stinging sensations in users with small wrists, while users with large wrists fail to achieve effective treatment due to insufficient stimulation depth. Even if some devices offer multi-level adjustment functions, parameter selection still relies on the user's subjective feeling, lacking objective physiological basis and a scientific adaptation mechanism.

[0007] Regarding feedback on treatment effectiveness, traditional electrical stimulation devices mostly operate in an open-loop control mode, meaning they continuously output stimulation according to preset parameters, failing to dynamically optimize these parameters based on the user's real-time physiological response. As the user develops neural adaptation, the effect of stimulation with fixed parameters gradually weakens, and the device cannot detect this change or proactively adjust the stimulation mode, leading to a decline in treatment effectiveness. Furthermore, the lack of real-time monitoring and feedback on physiological indicators such as sympathetic nerve tone prevents the device from assessing the effectiveness of treatment and optimizing subsequent stimulation strategies accordingly.

[0008] In summary, the existing technology lacks an intelligent electrical stimulation-assisted positioning system that can achieve self-sensing of electrode position, anti-interference acquisition of physiological signals, personalized adaptation of stimulation parameters, and closed-loop dynamic adjustment of treatment effects. Summary of the Invention

[0009] To address the aforementioned shortcomings, this invention proposes an electrical stimulation-assisted positioning wristband and its adjustment method based on a resistive trapezoidal network. This constructs an intelligent electrical stimulation-assisted positioning system that integrates location recognition and effect evaluation, significantly improving the accuracy, effectiveness, and user experience of electrical stimulation therapy.

[0010] This invention provides the following technical solution: an electrical stimulation-assisted positioning wristband based on a resistive trapezoidal network, used to achieve self-sensing of the position of the electrode module on the wristband, comprising: The host unit is equipped with a pulse generation circuit and a signal acquisition circuit; The functional watch strap includes an insulating watch strap base and at least two mutually insulated conductive conductors embedded in the insulating watch strap base. One end of the insulating watch strap base is connected to one end of the main unit, and the conductive conductors are electrically connected to the main unit. The conductive conductor includes a plurality of conductive vias arranged in an array along its length, and at least one conductive conductor has a fixed resistor integrated on a conductive substrate connected in series between adjacent conductive vias to form a resistance ladder network, such that each conductive via corresponds to an access node of the resistance ladder network with a unique internal resistance increment characteristic. An electrode module is set up one-to-one with a conductive conductor. The electrode module includes electrode sheets and conductive posts. An installation channel penetrating the thickness direction is provided on the insulating watch strap base at the position corresponding to the conductive through hole. The installation channel includes a conductive groove near the wearing part and a fixing groove away from the wearing part. The conductive post is detachably inserted into the mounting channel. One end of the post is connected to the electrode plate, and the other end is detachably connected to the fastener. This allows the electrode module to be fixed at any access point of the watch band, and the electrode plate to be electrically connected to the conductive conductor through the conductive post. This enables the host unit to uniquely identify the current physical location of the electrode module by detecting the internal resistance increment of the resistive ladder network.

[0011] As an improvement, the conductive groove is an insulating groove opened on the side of the insulating strap base near the wearing part, the depth of the insulating groove is not less than 1.5mm, and the conductive through hole is located at the bottom of the insulating groove.

[0012] As an improvement, the number N of conductive vias is related to the resistance value of the precision fixed resistor unit. The following impedance matching constraints must be met: in, The preset line impedance safety threshold is less than or equal to 10% of the lower limit of the characteristic impedance of human acupoints, and the resistance value of the precision fixed resistor unit is... The range is 100 to 1000 Ω, and the number of conductive vias N is 8 to 12 pairs.

[0013] As an improvement, the main unit also includes a multiplexing switching circuit and a charge discharge circuit. The multiplexing switching circuit is electrically connected to the pulse generation circuit, the signal acquisition circuit, and the charge discharge circuit, respectively. The multiplexing switching circuit is configured to connect the pulse generation circuit to the conductive conductor during the pulse output period and connect the charge discharge circuit to the conductive conductor during the signal acquisition period after the pulse output ends to release the accumulated charge. Subsequently, the signal acquisition circuit is connected to the conductive conductor to acquire the skin conduction response signal.

[0014] The adjustment method for an electrical stimulation-assisted positioning wristband based on a resistive trapezoidal network, applied to any of the aforementioned electrical stimulation-assisted positioning wristbands based on a resistive trapezoidal network, includes the following steps: S1. Physical location identification based on impedance decoupling: using the skin impedance measured by the user at the first reference jack position as the reference value. The total loop impedance of the acquisition electrode module at the current socket position. Calculate the difference , the difference Matching with a preset resistance ladder table to lock the current physical location number of the electrode module. ; Call and physical location number Corresponding preset value of line internal resistance And subtract the preset value of the line internal resistance from the real-time detection data. To obtain the decoupled net skin impedance ; S2. Precise acupoint positioning based on impedance feature recognition: Real-time monitoring of skin impedance during user adjustment of electrode module position. The change curve when net skin impedance is detected The electrode module is considered to be aligned with the target nerve stimulation point when both of the following conditions are met: (1) it falls within the preset nerve characteristic impedance range; (2) it exhibits local impedance minimum characteristics. S3. Adaptive initialization of stimulus parameters based on physical location: according to the physical location number locked in step S1. Based on the wristband segment, the system infers the user's wrist anatomy and retrieves the matching initial electrical stimulation waveform and intensity parameters from a pre-set parameter database. S4. Closed-loop dynamic adjustment based on skin conductance response: The control electrode module outputs the initial electrical stimulation waveform, and during the signal acquisition interval after each electrical pulse output ends, the accumulated charge is first released through the charge discharge circuit, and then the user's skin conductance response signal is acquired. Based on the trend of sympathetic nerve tension change represented by the skin conductance response signal, the output parameters of the subsequent electrical stimulation signal are adjusted in real time.

[0015] As an improvement, in step S1, the reference position is the first access node on the side adjacent to the host unit, and the preset value of the line internal resistance corresponding to the first access node is... It is zero.

[0016] As an improvement, in step S1, the difference is... Matching with a preset resistance ladder table to lock the current physical location number of the electrode module. Specifically, it includes: Get the preset resistance value of the resistor unit ; Construct a theoretical internal resistance value sequence corresponding to each access node { },in , Assign a location number to the access node; Determine the theoretical internal resistance values The corresponding matching interval is ( , ]; Judge the difference The matching interval that falls into the range is identified, and the corresponding position of that interval is numbered. The current physical location number of the electrode module is determined. ; If the difference Greater than the maximum theoretical internal resistance value and If the sum of the two values ​​is not equal, an anomaly is determined, and a recalibration is prompted.

[0017] As an improvement, in step S1, net skin impedance is obtained. Specifically, it includes: Based on the locked physical location number Retrieve the physical location number from the pre-stored impedance parameter table. The unique corresponding preset value of line internal resistance ; The total impedance of the circuit collected at the current socket position. With the preset value of the line internal resistance Perform decoupling operations. To remove the contamination of physiological signals by line resistance, the net skin impedance, which characterizes the true physiological state of the skin, is obtained. .

[0018] As an improvement, in step S2, the preset neural characteristic impedance range is 20kΩ to 50kΩ, which corresponds to the transcutaneous impedance characteristic value range of the Neiguan acupoint in the human body. When the net skin impedance... When the impedance falls within the range of 20kΩ to 50kΩ and exhibits a local minimum value characteristic relative to the impedance value of adjacent monitoring points, it is determined that the electrode has been aligned with the Neiguan acupoint stimulation point.

[0019] As an improvement, in step S3, the user's wrist anatomical features are estimated based on the wristband segment corresponding to the physical location number, specifically including: Obtain the physical location number locked in step S1 ; Determine the physical location number Belongs to the preset number range: like If the user belongs to the first numbering interval consisting of access nodes 1 to 4 on the side adjacent to the host unit, then the user is determined to be of the thin wrist type, which corresponds to the anatomical characteristics of a thin subcutaneous fat layer and a shallow target nerve location. like If the second numbering interval, which consists of access nodes 5 to 7 in the middle position, is used, then the user is determined to be of the standard wrist circumference type. like If the user belongs to the third numbering interval consisting of access nodes 8 and above on the side furthest from the host unit, then the user is determined to have a thick wrist circumference, which corresponds to the anatomical characteristics of a thicker subcutaneous fat layer and a deeper target nerve location.

[0020] As an improvement, in step S3, the initial electrical stimulation waveform and intensity parameters constitute a pre-configured parameter combination. The parameter combination is retrieved from a preset parameter database based on the user's wrist anatomical features estimated in step S3, so that the initial electrical stimulation parameters match the user's physiological structural features. The parameter combination includes at least the pulse waveform type, pulse width, output voltage amplitude, and basic pulse frequency. The pulse width and output voltage amplitude are positively correlated with the subcutaneous fat thickness estimated in step S3.

[0021] As an improvement, in step S3, the corresponding initial electrical stimulation waveform and intensity parameters are retrieved based on the user's wrist anatomical features, specifically including: When the user is identified as having a small wrist, the soft mode parameter set containing the first pulse width and the first output voltage is invoked; When the user is identified as having a standard wrist circumference, the standard mode parameter set, which includes the second pulse width and the second output voltage, is invoked. When a user is identified as having a large wrist circumference, the passthrough mode parameter set containing the third pulse width and the third output voltage is invoked; Among them, the first pulse width, the second pulse width, and the third pulse width increase sequentially, and the first output voltage, the second output voltage, and the third output voltage increase sequentially.

[0022] As an improvement, in step S4, the user's skin conductance response signal is acquired during the interval of the electrical pulse output, specifically including the following timing control steps: Pulse cutoff and path switching: After each electrical pulse output cycle, the connection between the pulse generating circuit and the conductive conductor is disconnected through a multiplexing switching circuit; Charge discharge: The charge discharge circuit is connected to the conductive conductor through a multiplexing switching circuit, and the electrode module is short-circuited to ground potential to release the residual charge accumulated on the skin surface and eliminate interference with subsequent signal acquisition. Signal acquisition: After the charge discharge is completed, the charge discharge circuit is disconnected through the multiplexing switching circuit, and the connection between the signal acquisition circuit and the conductive conductor is turned on. The skin conductivity at this time is collected as the skin conductance response signal.

[0023] As an improvement, in step S4, the output parameters of the subsequent electrical stimulation signal are dynamically adjusted based on the trend of sympathetic nerve tension changes characterized by the skin conductance response signal. Specifically, this includes: Calculate the time series of skin conductivity within a preset time window and fit it to obtain its slope K. The slope K is compared with a preset slope threshold, and different parameter adjustment strategies are executed based on the comparison result: If the slope K is less than the first preset threshold, it indicates that the sympathetic nerve tension is decreasing, which means that the current stimulation parameters are effective. In this case, the current output parameters are maintained or the stimulation intensity is reduced by a preset step size. If the slope K of the change is greater than or equal to the first preset threshold, it indicates that the sympathetic nerve tension has not decreased as expected or has developed neural adaptation. Then, the parameter adjustment mechanism is triggered. The adjustment mechanism includes at least one of the following methods: switching the stimulation frequency from the current base frequency to a preset high-frequency interference mode, increasing the stimulation intensity, or switching the stimulation waveform. Among them, the high-frequency interference mode continues for a preset duration before returning to the base frequency.

[0024] Compared with the prior art, the advantages of the present invention are as follows: This invention, through the deep coupling of structural design and methodological innovation, constructs a fully intelligent electrostimulation-assisted positioning system that integrates physical location perception, physiological signal acquisition, personalized parameter initialization, and closed-loop dynamic adjustment.

[0025] At the structural level, this invention embeds conductive conductors within the functional band and connects fixed resistors in series between adjacent conductive vias to form a resistive ladder network, making each conductive via a unique access node with a unique internal resistance increment. This allows the host unit to uniquely identify the current physical location of the electrode module by detecting the internal resistance increment, achieving self-sensing of electrode position and laying the hardware foundation for subsequent personalized adjustments. The conductive groove, as an insulating recess with a depth of not less than 1.5mm, with the conductive vias located at the bottom of the groove, effectively blocks the direct electrical connection between the skin's sweat layer and the conductive vias, avoiding signal leakage and crosstalk caused by sweat, and ensuring the accuracy of position recognition and physiological signal acquisition. The number of conductive vias and the resistance value of the fixed resistors meet specific impedance matching constraints, with the circuit impedance safety threshold being less than or equal to 10% of the lower limit of the characteristic impedance of human acupoints. This ensures a high signal-to-noise ratio in the detection circuit during the position recognition step and prevents the internal resistance increment of the circuit from masking the low impedance valley characteristics of acupoints during the acupoint locating step. The multiplexing switching circuit and charge discharge loop enable the host unit to precisely switch between the pulse output period, the charge discharge period, and the signal acquisition period. It discharges residual charge before acquiring signals, effectively eliminating the interference of charge accumulated on the skin surface by the electrical pulse output on subsequent physiological signal acquisition, and ensuring the purity and reliability of the skin electroreaction signal.

[0026] At the methodological level, this invention first uses the skin impedance measured at a reference position as a baseline value, collects the total circuit impedance at the current socket position and calculates the difference. This difference is then matched with a preset resistance ladder table to lock the physical position number of the electrode module. Next, the preset value of the line internal resistance corresponding to this number is called and subtracted from the real-time detection data to obtain the decoupled net skin impedance. This position identification and decoupling process eliminates the line impedance differences introduced by different electrode positions, ensuring that subsequent physiological signal analysis is no longer contaminated by line resistance and restoring the true physiological state of the skin. During the user's adjustment of the electrode module position, the change curve of the net skin impedance is monitored in real time. When the net skin impedance falls within a preset neural characteristic impedance range and exhibits local minimum characteristics, it is determined that the electrode is aligned with the target nerve stimulation point. This acupoint precise positioning method based on impedance feature identification overcomes the ambiguity of traditional methods relying on visual positioning or experience-based judgment, enabling the electrode to accurately cover nerve stimulation points such as the Neiguan acupoint, ensuring the effectiveness of electrical stimulation therapy. Based on the wristband segment where the locked physical location number is located, the user's wrist anatomy is inferred in reverse. If it belongs to the first numbered interval adjacent to the host unit, it is determined to be a user with a thin wrist circumference, corresponding to thin subcutaneous fat and shallow nerve location. If it belongs to the second numbered interval in the middle position, it is determined to be a user with a standard wrist circumference. If it belongs to the third numbered interval far from the host unit, it is determined to be a user with a thick wrist circumference, corresponding to thick subcutaneous fat and deep nerve location. Then, based on the anatomical characteristics, the matching initial electrical stimulation waveform and intensity parameters are retrieved from the preset parameter database. This physical location-based adaptive initialization method of stimulation parameters achieves a positive correlation between stimulation intensity and fat thickness, allowing users with thin wrist circumferences to receive gentle stimulation to avoid stinging sensations, and users with thick wrist circumferences to receive strong penetration to ensure stimulation depth. This solves the problem that the fixed parameters of traditional electrical stimulation devices cannot adapt to individual differences.

[0027] In the closed-loop adjustment stage, during the signal acquisition interval after each electrical pulse output, the accumulated charge is first released through a charge discharge circuit, and then skin conductivity is acquired as the skin electrical response signal. The slope of the skin conductivity change within a preset time window is calculated and compared with a preset threshold. If the slope is less than the first preset threshold, indicating a decreasing trend in sympathetic nerve tension, the current stimulation parameters are effective. In this case, the current output parameters are maintained or the stimulation intensity is decreased by a preset step size to achieve cruise pressure maintenance. If the slope is greater than or equal to the first preset threshold, indicating that the sympathetic nerve tension has not decreased as expected or has developed neural adaptation, a parameter adjustment mechanism is triggered, including at least one of the following: switching the stimulation frequency from the current base frequency to a preset high-frequency interference mode, increasing the stimulation intensity, or switching the stimulation waveform. The high-frequency interference mode is maintained for a preset duration and then returns to the base frequency. This closed-loop dynamic adjustment method based on skin electrical response enables the electrical stimulation system to sense the user's physiological response state in real time and dynamically optimize the output parameters. When the treatment is effective, the intensity is maintained or reduced to save energy and prolong comfort. When the treatment is ineffective or adaptation occurs, active intervention is used to break neural tolerance, ensuring the continuous and stable treatment effect.

[0028] In summary, this invention achieves self-sensing of electrode position through a resistive trapezoidal network, restores real skin impedance through impedance decoupling technology, achieves precise acupoint positioning through impedance feature recognition, realizes personalized parameter initialization by inferring anatomical features from physical position, ensures signal quality through timing control of stimulation-discharge-acquisition, and achieves closed-loop dynamic adjustment through skin electroreactivity slope threshold judgment. This forms a complete technical solution from hardware structure to software algorithm, from position recognition to effect evaluation. It enables the smart bracelet to automatically sense electrode position, accurately locate acupoints, adapt to individual anatomical features, and optimize stimulation parameters in real time, significantly improving the accuracy, effectiveness, and user experience of electrostimulation therapy. It overcomes many technical shortcomings of traditional smart bracelets, such as fixed electrode positions that cannot adapt to users with different wrist sizes, circuit impedance contamination of physiological signals, one-size-fits-all stimulation parameters that cannot be individualized, and open-loop treatment processes that cannot be dynamically optimized. This invention has significant technological advancements and clinical application value in the field of smart wearable health management. Attached Figure Description

[0029] The present invention will be further described in detail below with reference to the accompanying drawings and specific embodiments: Figure 1 An exploded view of the structure of an electrical stimulation-assisted positioning wristband based on a resistor trapezoidal network; Figure 2 A first-view structural diagram of an electrically stimulated positioning wristband based on a resistive trapezoidal network; Figure 3 A schematic diagram of the second-view structure of an electrical stimulation-assisted positioning wristband based on a resistive trapezoidal network; Figure 4 The flowchart shows the adjustment method of the wristband of an electrical stimulation-assisted positioning bracelet based on a resistive trapezoidal network. Figure 5 The impedance values ​​collected by adjusting the positions of the electrode modules sequentially along the watch band are shown in the figure. The position of the H4 jack is indicated as an acupoint. Figure 6 This is a diagram showing the impedance distribution around the acupoint.

[0030] The markings in the above figures are as follows: 1. Functional watch band; 1.1. Insulating watch band base; 1.1.1. Conductive groove; 1.1.2. Fixing groove; 1.2. Conductive conductor; 1.2.1. Conductive through hole; 1.3. Fixed resistor; 2. Electrode module; 2.1. Electrode sheet; 2.2. Conductive post; 2.3. Fixing component. Detailed Implementation

[0031] In this invention, it should be understood that the terms "length", "width", "upper", "lower", "front", "rear", "left", "right", "vertical", "horizontal", "top", "bottom", "inner", "outer", "clockwise", "counterclockwise", "axial", "planar direction", "circumferential", etc., indicating the orientation or positional relationship, are based on the orientation or positional relationship shown in the accompanying drawings, and are only for the convenience of describing this invention and simplifying the description, and are not intended to indicate or imply that the device or element referred to must have a specific orientation, or be constructed and operated in a specific orientation, and therefore should not be construed as a limitation of this invention.

[0032] like Figures 1 to 3 As shown, the electrical stimulation-assisted positioning wristband based on a resistive trapezoidal network is used to realize the self-sensing of the position of the electrode module 2 on the wristband, including a host unit, a functional wristband 1, and an electrode module 2.

[0033] The host unit is equipped with a pulse generation circuit and a signal acquisition circuit for generating low-frequency electrical pulses and acquiring physiological signals. In a preferred embodiment, the host unit also includes a multiplexing switching circuit and a charge discharge circuit. The multiplexing switching circuit is electrically connected to the pulse generation circuit, the signal acquisition circuit, and the charge discharge circuit, respectively, and is configured to connect the corresponding circuit to the conductive conductor 1.2 at different operating times to achieve time-division multiplexing.

[0034] The functional watch band 1 includes an insulating watch band base 1.1 and at least two mutually insulated conductive conductors 1.2 embedded within the insulating watch band base 1.1. One end of the insulating watch band base 1.1 is connected to one end of the host unit, and the conductive conductors 1.2 are electrically connected to the host unit for transmitting electrical pulses and physiological signals between the host unit and the electrode module 2. The conductive conductor 1.2 includes a conductive substrate and a plurality of conductive vias 1.2.1 arrayed along the length of the conductive substrate. Specifically, a fixed resistor 1.3 integrated on the conductive substrate is connected in series between adjacent conductive vias 1.2.1 of at least one conductive conductor 1.2, thereby forming a resistance ladder network. This resistance ladder network makes each conductive via 1.2.1 correspond to an access node with a unique internal resistance increment characteristic. When the electrode module 2 is inserted into different conductive vias 1.2.1, the host unit can uniquely identify the current physical position of the electrode module 2 by detecting the internal resistance increment of the node.

[0035] Preferably, the number N of conductive vias 1.2.1 is 8 to 12 pairs, and the resistance of the fixed resistor 1.3 is... The resistance is between 100Ω and 1000Ω, more preferably, this resistance value The resistance ranges from 100Ω to 300Ω. Simultaneously, the number N of conductive vias 1.2.1 and the resistance value of the fixed resistor 1.3... The following impedance matching constraints must be met: in, A preset line impedance safety threshold is defined, which is less than or equal to 10% of the lower limit of the characteristic impedance of acupoints on the human body. In this embodiment, the line impedance safety threshold... The preferred impedance is 2500Ω. This design ensures that the high signal-to-noise ratio of the detection loop is maintained during the location identification step, and prevents the increase in line internal resistance from masking the low impedance valley characteristics of the hole during the hole finding step.

[0036] Electrode modules 2 are configured one-to-one with conductive conductors 1.2. Each electrode module 2 includes an electrode sheet 2.1 and a conductive post 2.2. The electrode sheet 2.1 is used to adhere to the user's skin, and the conductive post 2.2 is used to achieve electrical connection and mechanical fixation. An installation channel penetrating the thickness direction is formed on the insulating strap base 1.1 at the position corresponding to the conductive through-hole 1.2.1. This installation channel includes a conductive groove 1.1.1 near the wearing area and a fixing groove 1.1.2 away from the wearing area. The conductive post 2.2 is detachably inserted into the installation channel, with one end connected to the electrode sheet 2.1 and the other end detachably connected to the fixing member 2.3. During installation, the conductive post 2.2 passes sequentially through the conductive groove 1.1.1 and the conductive through-hole 1.2.1, and is locked with the fixing member 2.3, thereby fixing the electrode module 2 at any access point of the functional strap 1, and simultaneously enabling the electrode sheet 2.1 to achieve electrical connection with the conductive conductor 1.2 through the conductive post 2.2. With this structure, users can freely adjust the position of electrode module 2 according to their wrist circumference to ensure that the electrodes accurately cover the target stimulation area.

[0037] The conductive groove 1.1.1 is an insulating groove formed on the side of the insulating strap base 1.1 near the wearing part. The depth of the insulating groove is not less than 1.5mm, and the conductive through hole 1.2.1 is located at the bottom of the insulating groove. This design can effectively block the direct electrical connection between the skin sweat layer and the conductive through hole 1.2.1, avoid signal leakage and crosstalk caused by sweat, and ensure the accuracy of position recognition and physiological signal acquisition.

[0038] In practical applications, the host unit controls the operating mode through a multiplexing switching circuit. During the pulse output period, the multiplexing switching circuit connects the pulse generation circuit to the conductive conductor 1.2, allowing the electrical pulse to be transmitted to the electrode module 2 via the conductive conductor 1.2 to stimulate the user's acupoints. During the signal acquisition period after the pulse output ends, the multiplexing switching circuit first disconnects the pulse generation circuit and connects the charge discharge circuit to the conductive conductor 1.2, shorting the electrode module 2 to ground potential to release the residual charge accumulated on the skin surface. After the charge discharge is completed, the multiplexing switching circuit disconnects the charge discharge circuit and connects the signal acquisition circuit to the conductive conductor 1.2, acquiring the skin conductivity at this time as the skin electroreactivity signal. This timing control effectively eliminates the interference of residual charge on the physiological signal acquisition, ensuring the purity of the signal.

[0039] like Figures 4 to 6 As shown, based on the aforementioned electrically stimulated positioning wristband strap based on a resistive trapezoidal network, the present invention also provides an adjustment method for the wristband strap, the method comprising the following steps.

[0040] In step S1, physical location identification based on impedance decoupling is performed. The user first inserts the electrode module into the first access node on the side adjacent to the host unit, which is denoted as H1, and its corresponding line internal resistance is preset. The value is zero; the skin impedance measured by the host unit at this location is used as a reference value. Subsequently, the user moves the electrode module to the desired socket position, denoted as HX, and the host unit acquires the total loop impedance at that position. And calculate the difference. The host unit uses an interval matching algorithm to calculate the difference. The system matches the current physical location number of the electrode module against a preset resistance ladder table. Specifically, the preset resistance ladder table defines the resistance matching rules from the reference socket H1 to the target socket H10: with H1 as the reference, the ideal difference is 0Ω, and the ideal resistance difference for each subsequent socket H2 to H10 increases by 100Ω sequentially. For each target socket, a corresponding algorithm matching range is set: H1 corresponds to 0Ω to 50Ω, H2 to 51Ω to 150Ω, H3 to 151Ω to 250Ω, H4 to 251Ω to 350Ω, H5 to 351Ω to 450Ω, H6 to 451Ω to 550Ω, H7 to 551Ω to 650Ω, H8 to 651Ω to 750Ω, H9 to 751Ω to 850Ω, and H10 to 851Ω to 950Ω. The measurement tolerance for all sockets is ±50Ω. If the measurement difference... If the value is greater than 950Ω or is negative, it is considered abnormal, the measurement is invalid, and the user is prompted to recalibrate.

[0041] After the physical location is locked, the host unit uses the locked physical location number as the basis for the action. Specifically, the host unit obtains the preset resistance value of the resistor unit. Construct a theoretical internal resistance value sequence corresponding one-to-one with each access node { },in , Assign location numbers to the access nodes; determine the theoretical internal resistance values. The corresponding matching interval is ( , ]; Determine the difference The matching interval that falls into the range is identified, and the corresponding position of that interval is numbered. The current physical location number of the electrode module is determined. If the difference Greater than the maximum theoretical internal resistance value and If the sum is not equal to the sum of the values, a mismatch is determined, and a recalibration prompt is issued to the user. After physical location locking is completed, the host unit determines the matching based on the locked physical location number. Retrieve the physical location number from the pre-stored impedance parameter table. The unique corresponding preset value of line internal resistance For example, if the locked position is H3, then the preset value of the line internal resistance corresponding to H3 is called. Then, a real-time compensation formula is constructed. The total impedance of the circuit at the current socket position is collected. With the preset value of the line internal resistance Decoupling operations are performed to remove the contamination of physiological signals by line resistance, thereby restoring the net skin impedance that characterizes the true physiological state of the skin. This decoupling formula will be used in all subsequent steps to eliminate line resistance interference.

[0042] In step S2, precise acupoint positioning based on impedance feature recognition is performed. While the user fine-tunes the electrode module position along the strap, the main unit monitors the skin impedance in real time via signal acquisition circuitry. The curve showing the change in net skin impedance. The electrode module is considered to be aligned with the target nerve stimulation point when both of the following conditions are met: Condition 1, net skin impedance. The impedance falls within a preset range of 20kΩ to 50kΩ, corresponding to the transcutaneous impedance characteristic range of the Neiguan acupoint; Condition 2: Net skin impedance. The impedance values ​​at adjacent monitoring points exhibit local minima. For example, the impedance values ​​around the Neiguan acupoint are 20kΩ and 50kΩ radially, with a distinct impedance trough at the center of the acupoint. When both of these conditions are met, the host unit determines that the electrode is aligned with the Neiguan acupoint stimulation point and notifies the user of successful positioning via a prompt message.

[0043] In step S3, adaptive initialization of stimulus parameters based on physical location is performed. The host unit performs this initialization according to the physical location number locked in step S1. The wristband segment in question is used to infer the user's wrist anatomy. The specific inference rule is: if... The first segment, consisting of access nodes H1 to H4 on the side adjacent to the host unit, is identified as a user with a thin wrist circumference, corresponding to anatomical characteristics of thin subcutaneous fat and superficial nerve locations; if The second segment, consisting of access nodes H5 to H7 located in the middle, is identified as a standard wrist circumference user; if The third segment, consisting of access nodes H8 to H10 located on the side furthest from the main unit, is identified as belonging to users with large wrist circumferences, corresponding to anatomical features such as thick subcutaneous fat and deep nerve locations. Subsequently, the main unit retrieves matching initial electrical stimulation waveforms and intensity parameters from a preset parameter database based on the aforementioned anatomical features. The parameter database is configured according to the mapping relationship between aperture location, physiological characteristics, and electrical pulse parameters: apertures H1 to H3 are classified as the gentle zone, suitable for users with thinner wrists, thinner fat layers, and shallower nerve locations, with initial electrical pulse parameters set as pulse width 150μs, output voltage 15V, and fundamental frequency 1Hz; apertures H4 to H7 are classified as the standard zone, suitable for users with standard wrist circumferences and moderate tissue impedance, with initial electrical pulse parameters set as pulse width 200μs, output voltage 25V, and fundamental frequency 1Hz; apertures H8 and above are classified as the penetrating zone, suitable for users with larger wrists, thicker fat layers, and deeper nerve locations, with initial electrical pulse parameters set as pulse width 300μs, output voltage 40V, and fundamental frequency 1Hz. As a preferred embodiment, the pulse waveform uses an asymmetric bidirectional square wave to reduce electrochemical corrosion. For example, when the identification result is H3, i.e., a user with a small wrist circumference, the system loads the soft mode parameters, including an asymmetric bidirectional square wave, a pulse width of 150μs, an initial output voltage of 15V, and a fundamental frequency of 1Hz; when the identification result is H10, i.e., a user with a large wrist circumference, the system loads the penetration mode parameters, including a pulse width of 300μs, an initial output voltage of 40V, and a fundamental frequency of 1Hz.

[0044] In step S4, closed-loop dynamic adjustment based on skin conductance response is performed. The host unit controls the pulse generation circuit to output the initial electrical stimulation waveform called in step S3, which is transmitted to the electrode module via a conductive conductor to perform electrical stimulation treatment on the user's Neiguan acupoint. During the signal acquisition interval after each electrical pulse output ends, the host unit performs the following timing control steps through a multiplexing switching circuit: First, pulse cutoff and path switching are performed. After each electrical pulse output cycle, the connection between the pulse generation circuit and the conductive conductor is disconnected through the multiplexing switching circuit. Next, charge discharge is performed. The connection between the charge discharge circuit and the conductive conductor is opened through the multiplexing switching circuit, and the electrode module is short-circuited to ground potential to release residual charge accumulated on the skin surface and eliminate interference with subsequent signal acquisition. Finally, signal acquisition is performed. After charge discharge is completed, the charge discharge circuit is disconnected through the multiplexing switching circuit, and the connection between the signal acquisition circuit and the conductive conductor is opened. The skin conductivity at this time is acquired as the skin conductance response signal. The host unit calculates the slope K of the change in skin conductivity over the past minute and adjusts the output parameters of subsequent electrical stimulation signals in real time based on the trend of sympathetic nerve tension changes represented by this slope. If K is less than 0 and shows a significant downward trend, it indicates that sympathetic nerve tension is decreasing and blood vessels are beginning to dilate, indicating that the current stimulation parameters are effective. In this case, the current parameters are maintained or the voltage is slightly reduced to extend the battery life, entering a cruise-and-hold mode. If K is greater than or equal to 0, i.e., skin conductivity is increasing or fluctuating, it indicates that the user is still tense or has developed neural adaptation, triggering a parameter adjustment mechanism. This adjustment mechanism includes abruptly changing the stimulation frequency from the current base frequency of 1Hz to a high-frequency interference mode of 100Hz for 10 seconds, or increasing the output voltage from 30V to 40V to break neural adaptation and reactivate the parasympathetic nervous system.

[0045] Through the coordinated operation of steps S1 to S4 above, this invention achieves intelligent electrostimulation-assisted positioning and treatment throughout the entire process, from self-sensing of electrode position, precise acupoint positioning, personalized initialization of stimulation parameters to closed-loop dynamic adjustment of treatment effect.

[0046] The above description only illustrates the preferred embodiments of the present invention and should not be construed as limiting the scope of the claims. The present invention is not limited to the above embodiments, and variations in its specific structure are permitted. All modifications made within the scope of the independent claims of this invention are also within the scope of protection of this invention.

Claims

1. A wristband for electrical stimulation-assisted positioning based on a resistive trapezoidal network, used to achieve self-sensing of the position of the electrode module on the wristband, characterized in that, include: The host unit is equipped with a pulse generation circuit and a signal acquisition circuit; The functional watch strap includes an insulating watch strap base and at least two mutually insulated conductive conductors embedded in the insulating watch strap base. One end of the insulating watch strap base is connected to one end of the main unit, and the conductive conductors are electrically connected to the main unit. The conductive conductor includes a plurality of conductive vias arranged in an array along its length, and at least one of the conductive conductors has a fixed resistor integrated on a conductive substrate connected in series between adjacent conductive vias to form a resistance ladder network, such that each conductive via corresponds to an access node of the resistance ladder network with a unique internal resistance increment characteristic. An electrode module is provided, corresponding one-to-one with the conductive conductor, and the electrode module includes electrode sheets and conductive posts; The insulating watch strap substrate has an installation channel extending through its thickness at the position corresponding to the conductive through hole. The installation channel includes a conductive groove near the wearing part and a fixing groove away from the wearing part. The conductive post is detachably inserted into the mounting channel, with one end connected to the electrode plate and the other end detachably connected to the fixing member, so that the electrode module is fixed at any of the access nodes of the watch band, and the electrode plate is electrically connected to the conductive conductor through the conductive post, thereby enabling the host unit to uniquely identify the current physical location of the electrode module by detecting the internal resistance increment of the resistive trapezoidal network.

2. The electrostimulation-assisted positioning wristband strap based on a resistive trapezoidal network according to claim 1, characterized in that, The conductive groove is an insulating groove formed on the side of the insulating watch strap base near the wearing part. The depth of the insulating groove is not less than 1.5mm, and the conductive through hole is located at the bottom of the insulating groove.

3. The electrostimulation-assisted positioning wristband strap based on a resistive trapezoidal network according to claim 1, characterized in that, The number N of the conductive vias and the resistance value of the precision fixed resistor unit The following impedance matching constraints must be met: in, The preset line impedance safety threshold is less than or equal to 10% of the lower limit of the characteristic impedance of human acupoints, and the resistance value of the precision fixed resistor unit is... The range is 100 to 1000 Ω, and the number of conductive vias N is 8 to 12 pairs.

4. The electrostimulation-assisted positioning wristband strap based on a resistive trapezoidal network according to claim 1, characterized in that, The host unit also includes a multiplexing switching circuit and a charge discharge circuit. The multiplexing switching circuit is electrically connected to the pulse generation circuit, the signal acquisition circuit, and the charge discharge circuit, respectively. The multiplexing switching circuit is configured to connect the pulse generation circuit to the conductive conductor during the pulse output period, and to connect the charge discharge circuit to the conductive conductor during the signal acquisition period after the pulse output ends, so as to release the accumulated charge. Then, the signal acquisition circuit is connected to the conductive conductor to acquire the skin conduction response signal.

5. An adjustment method for an electrical stimulation-assisted positioning wristband based on a resistive trapezoidal network, applied to an electrical stimulation-assisted positioning wristband based on a resistive trapezoidal network as described in any one of claims 1 to 4, characterized in that, Includes the following steps: S1. Physical location identification based on impedance decoupling: using the skin impedance measured by the user at the first reference jack position as the reference value. The total loop impedance of the acquisition electrode module at the current socket position. Calculate the difference The difference Matching with a preset resistance ladder table to lock the current physical location number of the electrode module. ; Call the physical location number Corresponding preset value of line internal resistance And subtract the preset value of the line internal resistance from the real-time detection data. To obtain the decoupled net skin impedance ; S2. Precise acupoint positioning based on impedance feature recognition: Real-time monitoring of the skin impedance during user adjustment of electrode module position. The change curve, when the net skin impedance is detected. The electrode module is considered to be aligned with the target nerve stimulation point when both of the following conditions are met: (1) it falls within the preset nerve characteristic impedance range; (2) it exhibits local impedance minimum characteristics. S3. Adaptive initialization of stimulus parameters based on physical location: according to the physical location number locked in step S1. Based on the wristband segment, the user's wrist anatomy is inferred in reverse, and the matching initial electrical stimulation waveform and intensity parameters are retrieved from the preset parameter database according to the anatomy. S4. Closed-loop dynamic adjustment based on skin conductance response: The control electrode module outputs the initial electrical stimulation waveform, and during the signal acquisition interval after each electrical pulse output ends, the accumulated charge is first released through the charge discharge circuit, and then the user's skin conductance response signal is acquired. According to the trend of sympathetic nerve tension change represented by the skin conductance response signal, the output parameters of the subsequent electrical stimulation signal are adjusted in real time.

6. The adjustment method for the watchband of an electrical stimulation-assisted positioning bracelet based on a resistive trapezoidal network according to claim 5, characterized in that, In step S1, the reference position is the first access node on the side adjacent to the host unit, and the preset value of the line internal resistance corresponding to the first access node is... It is zero.

7. The method for adjusting the strap of an electrical stimulation-assisted positioning wristband based on a resistive trapezoidal network according to claim 5, characterized in that, In step S1, the difference is... Matching with a preset resistance ladder table to lock the current physical location number of the electrode module. Specifically, it includes: Get the preset resistance value of the resistor unit ; Construct a theoretical internal resistance value sequence corresponding to each access node { },in , Assign a location number to the access node; Determine the theoretical internal resistance values The corresponding matching interval is ( , ], and theoretical internal resistance value ≥0; Determine the difference The matching interval that falls into the range is identified, and the corresponding position of that interval is numbered. The current physical location number of the electrode module is determined. ; If the difference Greater than the maximum theoretical internal resistance value and If the sum of the two values ​​is not equal, an anomaly is determined, and a recalibration is prompted.

8. The method for adjusting the strap of an electrical stimulation-assisted positioning wristband based on a resistive trapezoidal network according to claim 5, characterized in that, In step S1, the net skin impedance is obtained. Specifically, it includes: Based on the locked physical location number Retrieve the physical location number from the pre-stored impedance parameter table. The unique corresponding preset value of line internal resistance ; The total impedance of the circuit collected at the current socket position. With respect to the preset value of the line internal resistance Perform decoupling operations. To remove the contamination of physiological signals by line resistance, the net skin impedance, which characterizes the true physiological state of the skin, is obtained. .

9. The method for adjusting the strap of an electrical stimulation-assisted positioning wristband based on a resistive trapezoidal network according to claim 5, characterized in that, In step S2, the preset neural characteristic impedance range is 20kΩ to 50kΩ, which corresponds to the transcutaneous impedance characteristic value range of the Neiguan acupoint in the human body. When the net skin impedance... When the impedance falls within the range of 20kΩ to 50kΩ and exhibits a local minimum value characteristic relative to the impedance value of adjacent monitoring points, it is determined that the electrode has been aligned with the Neiguan acupoint stimulation point.

10. The method for adjusting the strap of an electrical stimulation-assisted positioning wristband based on a resistive trapezoidal network according to claim 5, characterized in that, In step S3, estimating the user's wrist anatomical features based on the wristband segment corresponding to the physical location number specifically includes: Obtain the physical location number locked in step S1 ; Determine the physical location number Belongs to the preset number range: like If the user belongs to the first numbering interval consisting of access nodes 1 to 4 on the side adjacent to the host unit, then the user is determined to be of the thin wrist type, which corresponds to the anatomical characteristics of a thin subcutaneous fat layer and a shallow target nerve location. like If the second numbering interval, which consists of access nodes 5 to 7 in the middle position, is used, then the user is determined to be of the standard wrist circumference type. like If the user belongs to the third numbering interval consisting of access nodes 8 and above on the side furthest from the host unit, then the user is determined to have a thick wrist circumference, which corresponds to the anatomical characteristics of a thicker subcutaneous fat layer and a deeper target nerve location.

11. The adjustment method for the watchband of an electrical stimulation-assisted positioning bracelet based on a resistive trapezoidal network according to claim 10, characterized in that, In step S3, the initial electrical stimulation waveform and intensity parameters constitute a pre-configured parameter combination. The parameter combination is retrieved from a preset parameter database based on the user's wrist anatomical features estimated in step S3, so that the initial electrical stimulation parameters match the user's physiological structural features. The parameter combination includes at least the pulse waveform type, pulse width, output voltage amplitude, and basic pulse frequency. The pulse width and output voltage amplitude are positively correlated with the subcutaneous fat thickness estimated in step S3.

12. The method for adjusting the strap of an electrical stimulation-assisted positioning wristband based on a resistive trapezoidal network according to claim 11, characterized in that, In step S3, the corresponding initial electrical stimulation waveform and intensity parameters are retrieved based on the user's wrist anatomical features, specifically including: When the user is identified as having a small wrist, the soft mode parameter set containing the first pulse width and the first output voltage is invoked; When the user is identified as having a standard wrist circumference, the standard mode parameter set, which includes the second pulse width and the second output voltage, is invoked. When a user is identified as having a large wrist circumference, the passthrough mode parameter set containing the third pulse width and the third output voltage is invoked; The first pulse width, the second pulse width, and the third pulse width increase sequentially, as do the first output voltage, the second output voltage, and the third output voltage.

13. The method for adjusting the strap of an electrical stimulation-assisted positioning wristband based on a resistive trapezoidal network according to claim 5, characterized in that, In step S4, the user's skin conductance response signal is acquired during the interval of electrical pulse output, specifically including the following timing control steps: Pulse cutoff and path switching: After each electrical pulse output cycle ends, the connection between the pulse generating circuit and the conductive conductor is disconnected through the multiplexing switching circuit; Charge discharge: The charge discharge circuit is connected to the conductive conductor through the multiplexing switching circuit, and the electrode module is short-circuited to ground potential to release the residual charge accumulated on the skin surface and eliminate interference with subsequent signal acquisition. Signal acquisition: After the charge discharge is completed, the charge discharge circuit is disconnected through the multiplexing switching circuit, and the connection between the signal acquisition circuit and the conductive conductor is turned on, and the skin conductivity at this time is acquired as the skin electroreactivity signal.

14. The method for adjusting the strap of an electrical stimulation-assisted positioning wristband based on a resistive trapezoidal network according to claim 5, characterized in that, In step S4, dynamically adjusting the output parameters of the subsequent electrical stimulation signal based on the trend of sympathetic nerve tension changes characterized by the skin conductance response signal specifically includes: Calculate the time series of skin conductivity within a preset time window and fit it to obtain its slope K. The slope K is compared with a preset slope threshold, and different parameter adjustment strategies are executed based on the comparison result: If the slope K of the change is less than the first preset threshold, it indicates that the sympathetic nerve tension is decreasing, indicating that the current stimulation parameters are effective. Then, the current output parameters are maintained or the stimulation intensity is reduced by a preset step size. If the slope K of the change is greater than or equal to the first preset threshold, indicating that the sympathetic nerve tension has not decreased as expected or has developed neural adaptation, then the parameter adjustment mechanism is triggered. The adjustment mechanism includes at least one of the following methods: switching the stimulation frequency from the current base frequency to a preset high-frequency interference mode, increasing the stimulation intensity, or switching the stimulation waveform. The high-frequency interference mode continues for a preset duration before returning to the base frequency.

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