CN118022177B - Low-injury nerve electrical stimulation method and system - Google Patents
Low-injury nerve electrical stimulation method and system Download PDFInfo
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- A61N1/00—Electrotherapy; Circuits therefor
- A61N1/18—Applying electric currents by contact electrodes
- A61N1/32—Applying electric currents by contact electrodes alternating or intermittent currents
- A61N1/36—Applying electric currents by contact electrodes alternating or intermittent currents for stimulation
- A61N1/36014—External stimulators, e.g. with patch electrodes
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- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
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- A61B5/316—Modalities, i.e. specific diagnostic methods
- A61B5/389—Electromyography [EMG]
- A61B5/395—Details of stimulation, e.g. nerve stimulation to elicit EMG response
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- A61N1/04—Electrodes
- A61N1/0404—Electrodes for external use
- A61N1/0408—Use-related aspects
- A61N1/0452—Specially adapted for transcutaneous muscle stimulation [TMS]
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
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- A61N1/02—Details
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- A61N1/0404—Electrodes for external use
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Abstract
The invention relates to the technical field of nerve electrical stimulation, in particular to a low-damage nerve electrical stimulation method and system. And further fine-tuning the current magnitude of the electric stimulation process according to the feedback of the user to the electric stimulation process. The invention can switch in the operation process through the conductive salient points of the electrodes, thereby reducing the difficulty of searching the optimal electric stimulation part for users; and the nerve electrical stimulation damage in the using process is reduced by calculating the minimum energy value and obtaining the electrical stimulation parameter.
Description
Technical Field
The invention relates to the technical field of nerve electrical stimulation, in particular to a low-damage nerve electrical stimulation method and system.
Background
Neuromuscular electrical stimulation (Neuromuscular Electrical Stimulation, NMES for short) uses low frequency pulsed current to stimulate motor nerves or muscles as a means of treating various diseases. This treatment involves the delivery of an external current to the nerve fibers, which excites the nerve fiber activity, which in turn causes the controlled muscles to produce a contractile response. In order to achieve an effective electrical stimulation, the lowest current intensity and the shortest stimulation duration, the so-called threshold electrical stimulation, that causes nerve fiber or muscle activation must be achieved. In the process of neuromuscular electrical stimulation, the intensity and the stimulation duration of the current are adjusted, so that not only can the strength of muscles be effectively improved, but also muscle atrophy caused by inactivity can be prevented and treated, and the muscles can be trained to perform specific functional actions. However, the current electrical stimulation has the defects of inaccurate stimulation path/stimulation parameters, ambiguous mechanism, effective amplitude and the like, which cause the electrical stimulation to be generally accompanied by injury and complications, so that the parameters of the electrical stimulation process are necessary to be optimized to reduce the injury of the electrical stimulation process.
Disclosure of Invention
(1) Technical problem to be solved
It is an object of the present invention to provide low-injury neural electrical stimulation methods and systems to optimize electrical stimulation parameters of a neural electrical stimulation process to reduce injury to the electrical stimulation process.
(2) Technical proposal
To achieve the above object, in one aspect, the present invention provides a low-damage nerve electro-stimulation method, the method comprising:
Acquiring a myoelectric signal of a nerve or muscle area which is undergoing electrical stimulation treatment, filtering and denoising the myoelectric signal to obtain a filtered signal, and recording the filtered signal which is generated when the nerve or muscle contracts and exceeds a set amplitude threshold as an action signal; the electrical stimulation treatment is carried out by adhering a conductive patch electrode to the skin surface of a nerve or muscle area to be treated, the electromyographic signals are measured by a voltage sensor adsorbed to the skin surface of the nerve or muscle area to be treated, and the distance between the voltage sensor and the conductive patch electrode exceeds a set distance threshold; the conductive patch electrode comprises a flitch and an array conductive salient point arranged on the flitch, and the conductive salient point is used as a positive electrode and a negative electrode in a discharging process of electric stimulation treatment;
Gradually increasing the current of the electrical stimulation treatment according to a set step length in a direct current mode until the current is recorded as a first current value after an action signal generated by nerve or muscle contraction is monitored; maintaining the current of the electric stimulation treatment in a direct current mode and increasing the current to be twice the first current value, and recording the time length after the current is applied to generate the action signal as the first time value after the action signal generated by nerve or muscle contraction is monitored; the current of the electric stimulation treatment is acted in a pulse mode and under a plurality of groups of different pulse widths, the current of an action signal generated by monitoring nerve or muscle contraction is recorded as a second current value, and the pulse width is recorded as a second time value; the method comprises the steps of obtaining electrode parameters of a conductive patch electrode, namely obtaining an electrode distance between a positive electrode and a negative electrode formed by the conductive bump, and obtaining a contact area of the conductive patch electrode for discharging; obtaining a fitting relation between the second current value and the second time value of the current of the electric stimulation treatment in a pulse mode through the second current value, the second time value and the electrode parameter;
Integrating the instantaneous power value on a time axis to obtain an energy value in a set time period through a second current value, wherein the formula of the energy value takes the second current value and the second time value as independent variables, the formula of the energy value derives the second time value to obtain a second current value and a second time value when the extremum of the energy value is the minimum energy value, and the second current value and the second time value are used as current parameters of electric stimulation treatment;
Holding a pressure tester, which is a pressure sensor held or clasped by a user and used for sensing the tension of the user, by the user who is undergoing the electrical stimulation treatment; and when the pressure value of the pressure tester exceeds a set pressure threshold, activating and applying electricity to adjacent conductive bumps of the conductive bumps which are currently applied, keeping a current second time value and obtaining a corrected second current value through the fitting relation between the second current value and the second time value.
Further, the method for filtering and denoising the electromyographic signals to obtain filtered signals comprises the following steps:
Converting the electromyographic signals into digital signals through an AD converter, then processing the digital signals through a band-pass filter to obtain first signals, and performing fast Fourier transform on the first signals to obtain a frequency spectrum distribution diagram; removing frequency components with energy exceeding the energy threshold value in the frequency spectrum distribution diagram based on a preset energy threshold value to obtain a second signal; performing inverse fast fourier transform on the second signal, and converting the second signal from the frequency domain back to the time domain to obtain a third signal; performing Hilbert transformation on the third signal, calculating the instantaneous amplitude and phase of the third signal on a time sequence, and marking the phase mutation point as a characteristic point on the time sequence; and carrying out interpolation processing on the amplitude values in the time period between the marked characteristic points and connecting the interpolated characteristic points to obtain a filtered signal.
Further, before pulsing the electrical current of the electrical stimulation therapy and at a plurality of different sets of pulse widths, the method further comprises:
And applying current in a direct current mode and a first current value, respectively applying and activating positive and negative electrodes formed by the conductive bumps according to the divided subareas, respectively testing a first time value after action signals generated by nerve or muscle contraction corresponding to the subareas, and taking the conductive bumps corresponding to the subareas when the first time value is minimum as the positive and negative electrodes of the electric stimulation treatment.
Further, the method for obtaining the fitting relation between the second current value and the second time value of the current of the electric stimulation treatment in a pulse mode through the second current value, the second time value and the electrode parameter comprises the following steps:
Establishing a fitting relation between a second current value and a second time value and marking the fitting relation as a first formula, wherein the first formula is as follows:
Wherein I 2 is a second current value, I 1 is a first current value, T 1 is a first time value, T 2 is a second time value, λ is a correction coefficient, ρ is a resistivity of a current flowing from the positive electrode through the negative electrode of the nerve or muscle to be treated, Z is an impedance of a current flowing from the positive electrode through the negative electrode of the nerve or muscle to be treated, d is an electrode distance, and a is a contact area; the electrode distance and the contact area are obtained by the conductive convex points in the state of power-on activation;
The current of the electric stimulation treatment is acted in a pulse mode under a plurality of groups of different pulse widths to obtain a second current value and a second time value, and the corresponding nerve or muscle to be treated is obtained through a first formula Is a value of (2).
Further, the method for activating and applying the adjacent conductive bumps of the currently applied conductive bumps, maintaining the current second time value and obtaining the corrected second current value through the fitting relation between the second current value and the second time value comprises the following steps:
After activating adjacent conductive bumps of the conductive bumps which are currently electrified, counting the distance between the centers of positive and negative electrodes of the current conductive bumps and updating the distance to be the electrode distance d, counting the number of the current conductive bumps to further obtain the contact area A of the conductive bumps and the nerve or muscle negative electrode to be treated and updating the contact area A; keeping the current second time value unchanged, and obtaining an updated second current value through a first formula; taking the second time value and the updated second current value as current parameters of the current electrical stimulation treatment;
the method for activating the adjacent conductive bumps of the current conductive bumps comprises the steps of firstly selecting according to the number of the newly-increased conductive bumps to approach the center of the anode and the cathode until the action signals generated by nerve or muscle contraction are monitored and the pressure value of the pressure tester does not exceed the set pressure threshold.
Further, the method for obtaining the second current value and the second time value when the extreme value of the energy value, that is, the minimum energy value, is obtained by integrating the instantaneous power value on the time axis by the second current value and obtaining the energy value in the set time period, wherein the formula of the energy value uses the second current value and the second time value as independent variables, and the formula of the energy value derives the second time value, namely the second current value and the second time value when the energy value is the extreme value of the energy value comprises the following steps:
the formula for calculating the instantaneous power value and integrating the instantaneous power value on a time axis to obtain the energy value E in a set time period is as follows:
And deriving the formula of the energy value E from the second time value to obtain a second time value T 2 corresponding to the extremum of the energy value, namely the minimum energy value E min, which is equal to the first time value T 1, and obtaining a second current value through the first formula according to the second time value.
Further, the method for selecting the direction of approaching the centers of the positive electrode and the negative electrode according to the set number of the newly added conductive bumps comprises the following steps:
adding the newly added conductive convex points in the direction of approaching the centers of the positive electrode and the negative electrode, and calculating the distance between the centers of the positive electrode and the negative electrode of the conductive convex points, namely an electrode distance d; when the electrode distance d meets a second formula, stopping increasing the newly added conductive bumps in the direction of approaching the centers of the positive electrode and the negative electrode, wherein the second formula is as follows:
further, the array conductive bumps arranged on the flitch are in a rectangular array, and the long edge of the rectangular array is arranged along the direction of the nerve or muscle to be treated.
Further, the method for obtaining the electrode distance between the anode and the cathode formed by the conductive bump comprises the following steps:
Establishing a coordinate system, obtaining the center coordinates of the conductive convex points, summing the center coordinates of the conductive convex points which form positive electrode power application at present and taking an average value as the electrode center of the positive electrode, and summing the center coordinates of the conductive convex points which form negative electrode power application at present and taking an average value as the electrode center of the negative electrode; the distance between the electrode center of the positive electrode and the electrode center of the negative electrode is taken as the electrode distance.
Based on the same inventive concept, in another aspect, the present invention also provides a low-damage nerve electro-stimulation system, the system comprising:
The electromyographic signal acquisition module is used for acquiring electromyographic signals of the nerve or muscle area which is undergoing the electrical stimulation treatment, filtering and denoising the electromyographic signals to obtain filtered signals, and recording the size of the filtered signals when the nerve or the muscle is contracted as an action signal; the electrical stimulation treatment is carried out by adhering a conductive patch electrode to the skin surface of a nerve or muscle area to be treated, the electromyographic signals are measured by a voltage sensor adsorbed to the skin surface of the nerve or muscle area to be treated, and the distance between the voltage sensor and the conductive patch electrode exceeds a set distance threshold; the conductive patch electrode comprises a flitch and an array conductive salient point arranged on the flitch, and the conductive salient point is used as a positive electrode and a negative electrode in a discharging process of electric stimulation treatment;
The current parameter acquisition module is used for gradually increasing the current of the electrical stimulation treatment according to a set step length in a direct current mode until the current is recorded as a first current value after an action signal generated by nerve or muscle contraction is monitored; maintaining the current of the electric stimulation treatment in a direct current mode and increasing the current to be twice the first current value, and recording the time length after the current is applied to generate the action signal as the first time value after the action signal generated by nerve or muscle contraction is monitored; the current of the electric stimulation treatment is acted in a pulse mode and under a plurality of groups of different pulse widths, the current of an action signal generated by monitoring nerve or muscle contraction is recorded as a second current value, and the pulse width is recorded as a second time value; the method comprises the steps of obtaining electrode parameters of a conductive patch electrode, namely obtaining an electrode distance between a positive electrode and a negative electrode formed by the conductive bump, and obtaining a contact area of the conductive patch electrode for discharging; obtaining a fitting relation between the second current value and the second time value of the current of the electric stimulation treatment in a pulse mode through the second current value, the second time value and the electrode parameter;
The stimulation energy calculating module is used for obtaining an instantaneous power value through a second current value, integrating the instantaneous power value on a time axis to obtain an energy value in a set time period, taking the second current value and the second time value as independent variables in the formula of the energy value, deriving the formula of the energy value over time to obtain a second current value and a second time value of the energy value when the extremum is the minimum energy value, and taking the second current value and the second time value as current parameters of electric stimulation treatment;
the comfort level feedback module is used for holding the pressure tester by a user who is undergoing electric stimulation treatment, and the pressure tester is a pressure sensor held or clamped by the user and used for sensing the tension level of the user; and when the pressure value of the pressure tester exceeds a set pressure threshold, activating and applying electricity to adjacent conductive bumps of the conductive bumps which are currently applied, keeping a current second time value and obtaining a corrected second current value through the fitting relation between the second current value and the second time value.
(3) Advantageous effects
Compared with the prior art, the invention has the beneficial effects that:
The conductive convex points of the electrodes can be switched in the operation process, so that the difficulty of searching the optimal electric stimulation part by a user is reduced; and the nerve electrical stimulation damage in the using process is reduced by calculating the minimum energy value and obtaining the electrical stimulation parameter.
Drawings
FIG. 1 is a flow chart of the low-damage nerve electro-stimulation method of embodiment 1 of the present invention;
Fig. 2 is a schematic diagram of the conductive patch electrode of embodiment 1 of the present invention attached to a forearm of a human body;
Fig. 3 is a schematic structural diagram of a conductive patch electrode according to embodiment 1 of the present invention;
FIG. 4 is a block diagram of a low-injury nerve stimulation system according to embodiment 2 of the present invention;
1-a conductive patch electrode; 2-forearm; 11-conductive bumps; 12-partitioning; 13-flitch; 14-positive electrode region; 15-negative pole region.
Detailed Description
The following description of the embodiments of the present invention will be made clearly and completely with reference to the accompanying drawings, in which it is apparent that the embodiments described are only some embodiments of the present invention, but not all embodiments. All other embodiments, which can be made by those skilled in the art based on the embodiments of the invention without making any inventive effort, are intended to be within the scope of the invention.
Before the present invention is illustrated, the application of the present invention is described, and the low-damage nerve stimulation uses the least energy to reduce the stimulation of muscle or nerve by external energy under the condition of meeting the requirement of stimulation treatment as far as possible. When the amplitude of the stimulation current is smaller, the cell is static and does not generate intracellular and extracellular action potentials; however, when the amplitude of the stimulating current is large, the cells generate spike signals, and the muscle or nerve cells macroscopically drive the associated muscle to shrink, so that the electromyographic signals generate action points. However, the larger the amplitude of the stimulation current, the better the stimulation current, but the smaller the energy value of the stimulation current, the less the damage caused by the electrical stimulation.
Example 1: as shown in fig. 1, the present embodiment provides a low-damage nerve electro-stimulation method, which includes:
S1, acquiring a myoelectric signal of a nerve or muscle area which is undergoing electric stimulation treatment, filtering and denoising the myoelectric signal to obtain a filtered signal, and recording the filtered signal which is generated when the nerve or muscle contracts and exceeds a set amplitude threshold as an action signal; the electrical stimulation treatment is carried out by adhering a conductive patch electrode to the skin surface of a nerve or muscle area to be treated, the electromyographic signals are measured by a voltage sensor adsorbed to the skin surface of the nerve or muscle area to be treated, and the distance between the voltage sensor and the conductive patch electrode exceeds a set distance threshold; the conductive patch electrode comprises a flitch and an array conductive salient point arranged on the flitch, and the conductive salient point is used as the positive electrode and the negative electrode of the discharge process of the electric stimulation treatment.
Illustratively, as shown in FIG. 2, it is assumed that a user suffers from carpal tunnel syndrome, with pain and numbness in the wrists and fingers. The method is used for electric stimulation treatment, firstly, the conductive patch electrode 1 is attached to the skin surface of the forearm 2 of a patient, and the electromyographic signals are obtained through a voltage sensor adsorbed on the skin surface. After the myoelectric signals are filtered and denoised, when signals generated by muscle contraction exceed a set threshold, the signals are recorded as action signals. When the amplitude of the stimulus current is small, the cell quiescence does not produce intracellular and extracellular action potentials, and the stimulus current is sought to be sufficient to cause the nerve or muscle to develop action potentials. The adsorption mode of the conductive patch electrode is various, and the conductive patch electrode can be adhered by binding and smearing conductive gel.
S2, gradually increasing the current of the electrical stimulation treatment in a direct current mode according to a set step length until the current is recorded as a first current value after an action signal generated by nerve or muscle contraction is monitored; maintaining the current of the electric stimulation treatment in a direct current mode and increasing the current to be twice the first current value, and recording the time length after the current is applied to generate the action signal as the first time value after the action signal generated by nerve or muscle contraction is monitored; the current of the electric stimulation treatment is acted in a pulse mode and under a plurality of groups of different pulse widths, the current of an action signal generated by monitoring nerve or muscle contraction is recorded as a second current value, and the pulse width is recorded as a second time value; the method comprises the steps of obtaining electrode parameters of a conductive patch electrode, namely obtaining an electrode distance between a positive electrode and a negative electrode formed by the conductive bump, and obtaining a contact area of the conductive patch electrode for discharging; and obtaining a fitting relation between the second current value and the second time value of the current of the electric stimulation treatment in a pulse mode through the second current value, the second time value and the electrode parameter.
The stimulation current applied by the user's forearm is typically stepped up in a direct current fashion until an action signal is detected, at which point the current level is recorded as a first current value, i.e., a reference current. It is noted that the minimum value of the current required to find the action potential at this time, that is, below the reference current, is insufficient to cause the action potential no matter how long the current stimulus is held. The holding current is twice the reference current until the motion signal is again monitored, and this time is recorded as a first time value. Since the current minimum is stimulated in a direct current manner, it means that the current in the form of pulses is at least twice as great as the stimulation intensity. The high level of the pulse signal typically accounts for half the pulse period, and this double the reference current is used to find the time when the nerve or muscle is producing an action potential. The nature of the action potential generated by the nerve or muscle is that the external stimulus has quite energy, in principle, when the stimulus current is increased, the time for generating the action potential is shortened, the stimulus with different current magnitudes is performed for a plurality of times, the pulse width for generating the action potential is obtained, namely, the second current value and the second time value have inverse functional relation, and the unknown coefficient of the functional relation is obtained through a plurality of groups of data. As shown in fig. 3, the conductive patch electrode 1 is divided into a positive electrode area 14 and a negative electrode area 15, the positive electrode area 14 or the negative electrode area 15 is further divided into a plurality of subareas 12, and each subarea is provided with a plurality of conductive bumps 11 in an array manner; the conductive bumps 11 are distributed on a non-conductive flitch 13.
S3, obtaining an instantaneous power value through a second current value, integrating the instantaneous power value on a time axis to obtain an energy value in a set time period, taking the second current value and the second time value as independent variables in a formula of the energy value, deriving the second time value from the formula of the energy value to obtain a second current value and a second time value when the extremum of the energy value is the minimum energy value, and taking the second current value and the second time value as current parameters of electric stimulation treatment.
The second current value is integrated on the time axis after a functional relation between the second current value and the second time value is obtained, and the minimum value of the energy value is obtained by taking the derivative of the second time value through an integration formula, so that the second current value is reversely obtained through the functional relation.
S4, holding a pressure tester by a user who is performing electric stimulation treatment, wherein the pressure tester is a pressure sensor held or clamped by the user and is used for sensing the tension degree of the user; and when the pressure value of the pressure tester exceeds a set pressure threshold, activating and applying electricity to adjacent conductive bumps of the conductive bumps which are currently applied, keeping a current second time value and obtaining a corrected second current value through the fitting relation between the second current value and the second time value.
For example, when the user performs the electrical stimulation treatment, although the extreme value of the energy value is found, if the user still experiences symptoms such as stinging after the pulse discharge of the electrical stimulation process, the user inevitably generates some stress response. When the user holds or clasps, the stress reaction causes the user to exert pressure on the held or clasped object, i.e., the pressure tester will feel the pressure. At this time, the number of the conductive bumps is increased, so that the current released by a single point can be reduced, and the stinging feeling in the electric stimulation process is reduced.
Further, the method for filtering and denoising the electromyographic signals to obtain filtered signals comprises the following steps:
Converting the electromyographic signals into digital signals through an AD converter, then processing the digital signals through a band-pass filter to obtain first signals, and performing fast Fourier transform on the first signals to obtain a frequency spectrum distribution diagram; removing frequency components with energy exceeding the energy threshold value in the frequency spectrum distribution diagram based on a preset energy threshold value to obtain a second signal; performing inverse fast fourier transform on the second signal, and converting the second signal from the frequency domain back to the time domain to obtain a third signal; performing Hilbert transformation on the third signal, calculating the instantaneous amplitude and phase of the third signal on a time sequence, and marking the phase mutation point as a characteristic point on the time sequence; and carrying out interpolation processing on the amplitude values in the time period between the marked characteristic points and connecting the interpolated characteristic points to obtain a filtered signal.
Illustratively, electrical stimulation therapy relies on accurate electromyographic signals to locate the exact active area of the muscle and to adjust the intensity and frequency of the electrical stimulation. The accurate acquisition of the electromyographic signals is the basis for later fine adjustment of the electrical stimulation parameters, but noise and interference in the signals can seriously affect the accuracy and reliability thereof. First, a voltage sensor is attached to an injured area of a forearm of a patient to collect an original myoelectric signal. The raw signal contains important information reflecting the muscle activity, but is also mixed with noise from other environmental factors. The specific process flow includes converting the electromyographic signals to digital signals via an AD converter and then processing them through a bandpass filter to reject noise above and below a specific frequency range of muscle activity. Next, the filtered signal is subjected to spectral analysis using a Fast Fourier Transform (FFT), further identifying and rejecting those frequency components that are abnormally high. Then, an inverse fast fourier transform is performed on the signal, it is converted from the frequency domain back to the time domain, and the instantaneous amplitude and phase are calculated by hilbert transform, so as to obtain a signal that more smoothly and accurately reflects the muscle activity, and extract the characteristic profile of the effective electromyographic signal.
Further, before pulsing the electrical current of the electrical stimulation therapy and at a plurality of different sets of pulse widths, the method further comprises:
And applying current in a direct current mode and a first current value, respectively applying and activating positive and negative electrodes formed by the conductive bumps according to the divided subareas, respectively testing a first time value after action signals generated by nerve or muscle contraction corresponding to the subareas, and taking the conductive bumps corresponding to the subareas when the first time value is minimum as the positive and negative electrodes of the electric stimulation treatment.
For example, the optimal location for applying a conductive patch electrode to a muscle or nerve has a degree of difficulty that a non-medical person who is not severely trained can only be roughly informed of the location where the conductive patch electrode should be applied. The conductive bumps of each partition are started and current is applied through repeated attempts of the array conductive bumps in the applied muscle area, and the time value after action signals generated by muscle contraction are recorded. The goal is to find the area with the shortest response time when current is applied, as this indicates that the muscle is most sensitive and effective to the response of electrical stimulation.
Further, the method for obtaining the fitting relation between the second current value and the second time value of the current of the electric stimulation treatment in a pulse mode through the second current value, the second time value and the electrode parameter comprises the following steps:
Establishing a fitting relation between a second current value and a second time value and marking the fitting relation as a first formula, wherein the first formula is as follows:
Wherein I 2 is a second current value, I 1 is a first current value, T 1 is a first time value, T 2 is a second time value, λ is a correction coefficient, ρ is a resistivity of a current flowing from the positive electrode through the negative electrode of the nerve or muscle to be treated, Z is an impedance of a current flowing from the positive electrode through the negative electrode of the nerve or muscle to be treated, d is an electrode distance, and a is a contact area; the electrode distance and the contact area are obtained by the conductive convex points in the state of power-on activation;
The current of the electric stimulation treatment is acted in a pulse mode under a plurality of groups of different pulse widths to obtain a second current value and a second time value, and the corresponding nerve or muscle to be treated is obtained through a first formula Is a value of (2).
Illustratively, in the scenario of the above-described forearm electrostimulation therapy, optimizing the therapy process by fine-tuning the current intensity and pulse width requires first modeling the relationship between current and pulse width. By continuous monitoring of the forearm electrostimulation process, a series of muscle electrostimulation data is collected, including the motor response of the muscle at different amperages and pulse widths. Using these data, a fitting relationship can be established by mathematical modeling methods, i.e., a first formula that considers the current intensity I 1、I2, the pulse width T 1、T2, and the resistivity ρ, impedance Z, electrode distance d, and contact area a of the muscle and skin, whereFor a particular muscle or nerve being treated, the value is a value that does not change much, and thus can be solved by the second time value and the second current value multiple times
Further, the method for activating and applying the adjacent conductive bumps of the currently applied conductive bumps, maintaining the current second time value and obtaining the corrected second current value through the fitting relation between the second current value and the second time value comprises the following steps:
After activating adjacent conductive bumps of the conductive bumps which are currently electrified, counting the distance between the centers of positive and negative electrodes of the current conductive bumps and updating the distance to be the electrode distance d, counting the number of the current conductive bumps to further obtain the contact area A of the conductive bumps and the nerve or muscle negative electrode to be treated and updating the contact area A; keeping the current second time value unchanged, and obtaining an updated second current value through a first formula; taking the second time value and the updated second current value as current parameters of the current electrical stimulation treatment;
the method for activating the adjacent conductive bumps of the current conductive bumps comprises the steps of firstly selecting according to the number of the newly-increased conductive bumps to approach the center of the anode and the cathode until the action signals generated by nerve or muscle contraction are monitored and the pressure value of the pressure tester does not exceed the set pressure threshold.
For example, in the above-described forearm electrostimulation treatment, in order to further optimize the treatment parameters, in particular the current parameters are adjusted in real time during the treatment to cope with the patient's feedback on the tingling sensation. Assuming that the stress level of the patient is monitored during the treatment using the stress tester, if the patient is found to be stressed due to the excessively high electrical stimulation intensity, the contact area of the applied electricity can be increased, thereby reducing the discomfort of the patient, and then the corrected current value (second current value) required at a specific pulse width can be calculated according to the previously established first formula. The number of the newly added conductive bumps is selected in the direction of approaching the centers of the positive and negative electrodes, so that the intensity direction of the current is reduced, and the shorter the distance between the positive and negative electrodes is, the shorter the nerve or cell path which needs to be excited by the current is.
Further, the method for obtaining the second current value and the second time value when the extreme value of the energy value, that is, the minimum energy value, is obtained by integrating the instantaneous power value on the time axis by the second current value and obtaining the energy value in the set time period, wherein the formula of the energy value uses the second current value and the second time value as independent variables, and the formula of the energy value derives the second time value, namely the second current value and the second time value when the energy value is the extreme value of the energy value comprises the following steps:
the formula for calculating the instantaneous power value and integrating the instantaneous power value on a time axis to obtain the energy value E in a set time period is as follows:
And deriving the formula of the energy value E from the second time value to obtain a second time value T 2 corresponding to the extremum of the energy value, namely the minimum energy value E min, which is equal to the first time value T 1, and obtaining a second current value through the first formula according to the second time value.
Illustratively, in the case of the above-described forearm electrostimulation treatment, one of the key challenges faced is how to ensure that the therapeutic effect is achieved while minimizing potential damage to the patient's muscles. To address this problem, a method based on instantaneous power calculation and energy value minimization was introduced, which helps to precisely regulate the electrical stimulation intensity during treatment. By real-time monitoring of the current intensity and pulse width during treatment, the instantaneous power value over a given period of time can be calculated. The calculation of the instantaneous power value not only depends on the current intensity and the pulse width, but also considers the factors such as the resistivity, the inter-electrode distance and the contact area when the current passes through the muscle. By integrating the instantaneous power value over the time axis, the therapist can derive the total energy consumption throughout the treatment process, thereby assessing the energy efficiency ratio of the treatment.
Further, the method for selecting the direction of approaching the centers of the positive electrode and the negative electrode according to the set number of the newly added conductive bumps comprises the following steps:
adding the newly added conductive convex points in the direction of approaching the centers of the positive electrode and the negative electrode, and calculating the distance between the centers of the positive electrode and the negative electrode of the conductive convex points, namely an electrode distance d; stopping increasing the newly increased conductive bump in the direction approaching the center of the positive electrode and the negative electrode when the electrode distance d meets a second formula, wherein the second formula is that
Illustratively, during the course of the forearm electrostimulation treatment, the magnitude of the treatment current is controlled by adjusting the electrode distance formed between the conductive bumps, ensuring that the second current value I 2 is not less than the first current value I 1 at which the action potential is generated. Assuming that the first current value I 1 has been determined to be minimal to produce effective muscle stimulation at the beginning of the treatment, as the treatment proceeds, it may be desirable to reduce the electrode distance d between the positive and negative electrodes in order to increase the comfort of the treatment or to adjust the stimulation intensity according to the patient's specific response. A decrease in the distance between the positive and negative electrodes results in a decrease in the required current, so that the same stimulation effect can be produced at lower total currents. However, such a reduction in current intensity is limited. It must be ensured that the reduced second current value I 2 is not lower than the initially determined first current value I 1, in order to avoid a reduction to a level insufficient to produce effective muscle stimulation.
Further, the array conductive bumps arranged on the flitch are in a rectangular array, and the long edge of the rectangular array is arranged along the direction of the nerve or muscle to be treated.
Further, the method for obtaining the electrode distance between the anode and the cathode formed by the conductive bump comprises the following steps:
Establishing a coordinate system, obtaining the center coordinates of the conductive convex points, summing the center coordinates of the conductive convex points which form positive electrode power application at present and taking an average value as the electrode center of the positive electrode, and summing the center coordinates of the conductive convex points which form negative electrode power application at present and taking an average value as the electrode center of the negative electrode; the distance between the electrode center of the positive electrode and the electrode center of the negative electrode is taken as the electrode distance.
Example 2: based on the same inventive concept, as shown in fig. 4, the present embodiment further provides a low-damage nerve electro-stimulation system, the system comprising:
The electromyographic signal acquisition module is used for acquiring electromyographic signals of the nerve or muscle area which is undergoing the electrical stimulation treatment, filtering and denoising the electromyographic signals to obtain filtered signals, and recording the size of the filtered signals when the nerve or the muscle is contracted as an action signal; the electrical stimulation treatment is carried out by adhering a conductive patch electrode to the skin surface of a nerve or muscle area to be treated, the electromyographic signals are measured by a voltage sensor adsorbed to the skin surface of the nerve or muscle area to be treated, and the distance between the voltage sensor and the conductive patch electrode exceeds a set distance threshold; the conductive patch electrode comprises a flitch and an array conductive salient point arranged on the flitch, and the conductive salient point is used as a positive electrode and a negative electrode in a discharging process of electric stimulation treatment;
The current parameter acquisition module is used for gradually increasing the current of the electrical stimulation treatment according to a set step length in a direct current mode until the current is recorded as a first current value after an action signal generated by nerve or muscle contraction is monitored; maintaining the current of the electric stimulation treatment in a direct current mode and increasing the current to be twice the first current value, and recording the time length after the current is applied to generate the action signal as the first time value after the action signal generated by nerve or muscle contraction is monitored; the current of the electric stimulation treatment is acted in a pulse mode and under a plurality of groups of different pulse widths, the current of an action signal generated by monitoring nerve or muscle contraction is recorded as a second current value, and the pulse width is recorded as a second time value; the method comprises the steps of obtaining electrode parameters of a conductive patch electrode, namely obtaining an electrode distance between a positive electrode and a negative electrode formed by the conductive bump, and obtaining a contact area of the conductive patch electrode for discharging; obtaining a fitting relation between the second current value and the second time value of the current of the electric stimulation treatment in a pulse mode through the second current value, the second time value and the electrode parameter;
The stimulation energy calculating module is used for obtaining an instantaneous power value through a second current value, integrating the instantaneous power value on a time axis to obtain an energy value in a set time period, taking the second current value and the second time value as independent variables in the formula of the energy value, deriving the formula of the energy value over time to obtain a second current value and a second time value of the energy value when the extremum is the minimum energy value, and taking the second current value and the second time value as current parameters of electric stimulation treatment;
the comfort level feedback module is used for holding the pressure tester by a user who is undergoing electric stimulation treatment, and the pressure tester is a pressure sensor held or clamped by the user and used for sensing the tension level of the user; and when the pressure value of the pressure tester exceeds a set pressure threshold, activating and applying electricity to adjacent conductive bumps of the conductive bumps which are currently applied, keeping a current second time value and obtaining a corrected second current value through the fitting relation between the second current value and the second time value.
It should be noted that, regarding the system in the above embodiment, the specific manner in which the respective modules perform the operations has been described in detail in the embodiment regarding the method, and will not be described in detail herein.
Finally, it should be noted that: although the present invention has been described with reference to the foregoing embodiments, it will be apparent to those skilled in the art that modifications may be made to the embodiments described, or equivalents may be substituted for elements thereof, and any modifications, equivalents, improvements and changes may be made without departing from the spirit and principles of the present invention.
Claims (1)
1. A low-injury nerve electrical stimulation system, the system comprising:
The electromyographic signal acquisition module is used for acquiring electromyographic signals of nerve or muscle areas which are undergoing electrical stimulation treatment, filtering and denoising the electromyographic signals to obtain filtered signals, and the method for filtering and denoising the electromyographic signals to obtain the filtered signals comprises the steps of converting the electromyographic signals to obtain digital signals through an AD (analog-to-digital) converter, then processing the digital signals through a band-pass filter to obtain first signals, and performing fast Fourier transform on the first signals to obtain a frequency spectrum distribution diagram; removing frequency components with energy exceeding the energy threshold value in the frequency spectrum distribution diagram based on a preset energy threshold value to obtain a second signal; performing inverse fast fourier transform on the second signal, and converting the second signal from the frequency domain back to the time domain to obtain a third signal; performing Hilbert transformation on the third signal, calculating the instantaneous amplitude and phase of the third signal on a time sequence, and marking the phase mutation point as a characteristic point on the time sequence; interpolation processing is carried out on the amplitude values in the time period between the marked characteristic points, and the interpolated characteristic points are connected to obtain filtered signals; the magnitude of the filtered signal at the time of nerve or muscle contraction is noted as an action signal; the electrical stimulation treatment is carried out by adhering a conductive patch electrode to the skin surface of a nerve or muscle area to be treated, the electromyographic signals are measured by a voltage sensor adsorbed to the skin surface of the nerve or muscle area to be treated, and the distance between the voltage sensor and the conductive patch electrode exceeds a set distance threshold; the conductive patch electrode comprises a flitch and an array conductive salient point arranged on the flitch, and the conductive salient point is used as a positive electrode and a negative electrode in a discharging process of electric stimulation treatment; the array type conductive convex points arranged on the flitch are rectangular arrays, and the long edges of the rectangular arrays are arranged along the direction of the nerve or muscle to be treated;
The current parameter acquisition module is used for gradually increasing the current of the electrical stimulation treatment according to a set step length in a direct current mode until the current is recorded as a first current value after an action signal generated by nerve or muscle contraction is monitored; maintaining the current of the electric stimulation treatment in a direct current mode and increasing the current to be twice the first current value, and recording the time length after the current is applied to generate the action signal as the first time value after the action signal generated by nerve or muscle contraction is monitored; applying current in a direct current mode and a first current value, respectively applying and activating positive and negative electrodes formed by the conductive bumps according to divided subareas, respectively testing a first time value after action signals generated by nerve or muscle contraction corresponding to the subareas, and taking the conductive bumps corresponding to the subareas when the first time value is minimum as the positive and negative electrodes of the electric stimulation treatment; the current of the electric stimulation treatment is acted in a pulse mode and under a plurality of groups of different pulse widths, the current of an action signal generated by monitoring nerve or muscle contraction is recorded as a second current value, and the pulse width is recorded as a second time value; the method comprises the steps of obtaining electrode parameters of a conductive patch electrode, namely obtaining an electrode distance between a positive electrode and a negative electrode formed by the conductive bump, and obtaining a contact area of the conductive patch electrode for discharging; obtaining a fitting relation between the second current value and the second time value of the current of the electric stimulation treatment in a pulse mode through the second current value, the second time value and the electrode parameter; the method for obtaining the fitting relation between the second current value and the second time value of the current of the electric stimulation treatment in a pulse mode through the second current value, the second time value and the electrode parameter comprises the steps of establishing the fitting relation between the second current value and the second time value and marking the fitting relation as a first formula, wherein the first formula is as follows:
；
Wherein the method comprises the steps of At the second current value, the first current value,At the first current value,For the first time value of the first time period,For the value of the second time period,In order to correct the coefficient of the coefficient,For the resistivity of the current flowing from the positive electrode through the negative electrode of the nerve or muscle to be treated,To flow from the anode through the impedance of the nerve or muscle cathode to be treated,For the distance of the electrodes,Is the contact area; the electrode distance and the contact area are obtained by the conductive convex points in the state of power-on activation;
The current of the electric stimulation treatment is acted in a pulse mode under a plurality of groups of different pulse widths to obtain a second current value and a second time value, and the corresponding nerve or muscle to be treated is obtained through a first formula Is a value of (2); the method for obtaining the electrode distance between the anode and the cathode formed by the conductive convex points comprises the steps of establishing a coordinate system, obtaining the center coordinates of the conductive convex points, summing the center coordinates of the conductive convex points currently forming anode power-on and taking an average value as the electrode center of the anode, summing the center coordinates of the conductive convex points currently forming cathode power-on and taking an average value as the electrode center of the cathode; taking the distance between the electrode center of the positive electrode and the electrode center of the negative electrode as an electrode distance;
The stimulation energy calculating module is used for obtaining an instantaneous power value through a second current value, integrating the instantaneous power value on a time axis to obtain an energy value in a set time period, taking the second current value and the second time value as independent variables in the formula of the energy value, deriving the formula of the energy value over time to obtain a second current value and a second time value of the energy value when the extremum is the minimum energy value, and taking the second current value and the second time value as current parameters of electric stimulation treatment; the method for obtaining the instantaneous power value through the second current value, integrating the instantaneous power value on a time axis to obtain the energy value in a set time period, wherein the formula of the energy value takes the second current value and the second time value as independent variables, the formula of the energy value derives the second time value to obtain the extreme value of the energy value, namely the second current value and the second time value when the energy value is minimum, comprises the steps of calculating the instantaneous power value and integrating the instantaneous power value on the time axis to obtain the energy value in the set time period The formula of (2) is:
;
Energy value Deriving the second time value to obtain the extreme value of the energy value, i.e. the minimum energy valueCorresponding second time valueEqual to the first time valueObtaining a second current value according to the second time value through the first formula;
The comfort level feedback module is used for holding the pressure tester by a user who is undergoing electric stimulation treatment, and the pressure tester is a pressure sensor held or clamped by the user and used for sensing the tension level of the user; when the pressure value of the pressure tester exceeds a set pressure threshold, activating and applying electricity to adjacent conductive bumps of the conductive bumps which are currently applied, keeping a current second time value and obtaining a corrected second current value through the fitting relation between the second current value and the second time value; activating and applying current to adjacent conductive bumps of the currently applied conductive bumps, maintaining a current second time value, and obtaining a corrected second current value through a fitting relation between the second current value and the second time value, wherein the method comprises the steps of counting the distance between the centers of positive electrode and negative electrode of the currently applied conductive bumps and updating the distance to be the electrode distance after activating the adjacent conductive bumps of the currently applied conductive bumps Counting the number of the current conductive bumps to obtain the contact area of the conductive bumps and the nerve or muscle negative electrode to be treated, and updating the contact area to be the contact area; Keeping the current second time value unchanged, and obtaining an updated second current value through a first formula; taking the second time value and the updated second current value as current parameters of the current electrical stimulation treatment; the method for activating the adjacent conductive bumps of the current conductive bumps comprises the steps of firstly selecting according to the number of the newly-added conductive bumps to the direction of approaching the centers of the positive electrode and the negative electrode until the action signals generated by nerve or muscle contraction are monitored and the pressure value of the pressure tester does not exceed a set pressure threshold value; the method comprises increasing the number of the newly increased conductive bumps in the direction of approaching the positive and negative electrode centers, and calculating the distance between the positive and negative electrode centers of the conductive bumps, i.e. electrode distance; When the electrode distance isStopping adding the newly added conductive bump to the direction close to the center of the anode and the cathode when a second formula is satisfied, wherein the second formula is as follows:
。
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| CN104027111A (en) * | 2014-06-27 | 2014-09-10 | 哈尔滨工业大学 | Dual-purpose electrode and device and method adopting same to realize surface electromyogram extraction and transcutaneous electrical stimulation |
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