Three-dimensional electric field coupling modeling method for analgesia

Abstract

According to the three-dimensional electric field coupling modeling method for analgesia provided by the invention, the propagation process of an electric field in each physiological tissue is accurately simulated by constructing a multi-layer bionic tissue model, so that the accuracy and effect of analgesia treatment are improved; calculating the conductivity and dielectric constant of each layer of tissue, performing numerical simulation on electric field distribution by using a finite element analysis technology, optimizing electrode configuration and electrical stimulation parameters, and ensuring the uniformity and stability of the electric field of a target area; a neurophysiology model is integrated, the conduction law of nerve fiber action potential is dynamically simulated, the stimulation effect of electric field intensity on nerve fibers is quantitatively analyzed, analgesia parameters are further optimized, and accurate control over pain signal transmission is achieved. The problems that in an existing electrical stimulation technology, electric field distribution is not uniform, electrode contact is not stable, and the stimulation effect is difficult to last are effectively solved, wide clinical application prospects are achieved, and an efficient, stable and accurate solution is provided especially in non-invasive treatment of chronic pain.

Description

Technical Field

[0001] The present invention relates to the technical fields of biomedical engineering and pain management, and particularly relates to a three-dimensional electric field coupling modeling method for analgesia. Background Art

[0002] Chronic pain is a common and complex pathological phenomenon in clinical practice, and its treatment has long been troubled by technical limitations. In recent years, surface electrical stimulation technology, as a non-invasive analgesic means, has received extensive attention due to its safety and low side effects. However, existing electrical stimulation technologies still have significant deficiencies in electric field control in multi-layer physiological tissues and optimization of nerve fiber responses.

[0003] Existing surface electrical stimulation technologies face the following challenges in application:

[0004] (1) The problem of uneven electric field distribution

[0005] Physiological tissues such as human skin, fat, muscle, and nerve fibers have significantly different electrical conductivities and dielectric constants, which makes it difficult to uniformly control the distribution of the electric field between tissues. Existing technologies usually rely on fixed electrode arrangement schemes and are difficult to optimize the distribution of the electric field in the target area, resulting in uneven activation or over-stimulation of nerve fibers, thus affecting the pain management effect.

[0006] (2) Lack of dynamic simulation of nerve fibers

[0007] Most existing electric field modeling technologies focus on static electric field distribution simulation and ignore the dynamic response characteristics of nerve fibers under different electrical stimulation conditions. The action potential conduction of nerve fibers is affected by multiple factors such as electric field strength, stimulation frequency, and impedance change, and its activation threshold and conduction characteristics need to be accurately described in dynamic modeling. Otherwise, it is difficult to effectively regulate the conduction of pain signals.

[0008] (3) Insufficient model accuracy and adaptability

[0009] In complex multi-layer physiological tissues, the accuracy of electric field distribution is often limited by finite model boundary conditions and simulation methods. Existing methods have not fully utilized finite element analysis technology to optimize the gradient distribution of complex electric fields. Especially for the individual electrophysiological characteristics of skin and nerve tissues, there is still a lack of a comprehensive optimization strategy to improve model adaptability. Summary of the Invention

[0010] The present invention is made to solve the above problems, and aims to provide a three-dimensional electric field coupling modeling method for analgesia, so as to solve the problems such as unstable electrode contact, uneven electric field distribution, and inaccurate nerve fiber activation effect faced by existing technologies in the treatment of chronic pain.

[0011] The present invention provides a three-dimensional electric field coupling modeling method for analgesia, which has the following characteristics. Specifically, it includes the following steps: S1, constructing a three-dimensional bionic potential model. Based on Gauss's law and Maxwell's equations, by applying a voltage to the three-dimensional bionic potential model using a simulation electrode, the dielectric constants and conductivities of multi-layer physiological tissues are accurately simulated, so as to achieve accurate calculation of the electric field strength and current density distribution; S2, optimizing the electrode excitation conditions, and through the accurate calculation of the electric field strength and current density distribution, ensuring the uniformity and stability of the electric field coverage, and obtaining a uniform and stable electric field distribution result; S3, combining with a neurophysiological model, inputting the electric field distribution result into the action potential conduction simulation module of nerve fibers, and by dynamically simulating the electrophysiological responses of nerve fibers to different electrical stimulation intensities, optimizing the electrical stimulation parameters, and finally achieving precise regulation of pain signal conduction. Among them, the three-dimensional bionic potential model is a multi-layer bionic tissue model including skin, fat, muscle, nerve and blood vessels, with a dielectric constant of ε r = 20 to 1500, and a conductivity of σ = 0.01 to 0.2 S / m. The electrode excitation conditions include the electrode spacing and surface contact resistance. The electrode spacing is 5 to 10 mm, and the surface contact resistance ≤ 500 Ω.

[0012] In the three-dimensional electric field coupling modeling method for analgesia provided by the present invention, it may also have the following characteristics: Among them, in step S1, the material of the simulation electrode is silver / silver chloride Ag / AgCl with excellent conductivity, combined with a conductive gel as the medium to maintain the long-term stability of the contact impedance. The conductivity of the conductive gel ≥ 1 S / m. The shape of the simulation electrode is controlled to be circular or oval, with a size range of 1 to 3 cm in diameter and a spacing of 5 to 10 mm, so as to achieve uniform distribution of the electric field in the optimized target area, and the current density of the simulation electrode is stably maintained at 0.05 to 0.1 A / m 2 , and the contact stability reaches more than 99%.

[0013] In the three-dimensional electric field coupling modeling method for analgesia provided by the present invention, it may further have the following characteristics: Among them, step S2 further includes the following sub-steps: S2-1, through the mesh refinement technology, comprehensively characterize the distribution characteristics of the high-gradient electric field in the complex physiological structure, obtain the electric field change law of the simulation-identified high-gradient region, and the mesh element size in the mesh refinement technology ≤ 0.01 mm; S2-2, based on the electric field change law of the simulation-identified high-gradient region, dynamically optimize the electrode position and voltage source parameters of the simulation electrode, adjust the electrode arrangement scheme of the simulation electrode, perform a detailed simulation on the three-dimensional bionic potential model, and obtain the simulation result, so as to maximize the uniformity of the electric field distribution in the three-dimensional bionic potential model, the voltage range is 0.5 - 1.5 V, and the electric field uniformity ≥ 93%; S2-3, based on the simulation result, further adjust the current density distribution of the simulation electrode, reduce the interference of the electric field non-uniformity on the nerve fiber response, thereby improving the accuracy and efficacy of the electrical stimulation, and finally establish a high-precision three-dimensional bionic potential model.

[0014] In the three-dimensional electric field coupling modeling method for analgesia provided by the present invention, it may further have the following characteristics: Among them, step S3 further includes the following sub-steps: S3-1, set the transmembrane capacitance of the nerve fiber to 1 μF / cm 2 , the activation threshold voltage is 0.5 V, the initial transmembrane potential is -70 mV, and simulate the action potential conduction response of the nerve fiber under the electric field intensity of 0.1 - 0.5 V / m; S3-2, simulate the transmembrane potential change process of the nerve fiber, quantify the conduction speed of the action potential of the nerve fiber, and analyze its dynamic stability under different physiological conditions through simulation, and the conduction speed is 50 - 80 m / s; S3-3, by adjusting the electrical stimulation intensity and frequency, optimize the transmembrane potential change process of the nerve fiber, significantly improve the efficiency and accuracy of the electrical stimulation, and optimize the electrical stimulation parameters.

[0015] In the three-dimensional electric field coupling modeling method for analgesia provided by the present invention, it may further have the following characteristics: Among them, in step S3-1, the calculation of the activation threshold voltage is based on the stimulation intensity (I stim ) and the electrophysiological characteristics of the nerve fiber, and the excitation threshold optimization formula is: Among them, σ takes a value of 0.05 S / m, d is the distance between the skin and the nerve fiber, set to 2 mm, V0 is the applied voltage, the range is 1 - 1.5 V, V threshold is the activation threshold voltage of the nerve fiber, taking a value of 0.5 V, and through iterative optimization, ensure that the nerve fiber is effectively activated under the threshold voltage.

[0016] In the three-dimensional electric field coupling modeling method for analgesia provided by the present invention, it may further have the following characteristics: Among them, in step S3-2, the transmembrane potential change of the nerve fiber is described by the following equation: Among them, C m is a membrane capacitance, with a value of 1 μF / cm 2 ; V m is the transmembrane potential, with an initial voltage of -70 mV and a maximum action potential of 30 mV; I m is the membrane current, and R m is the membrane resistance, with a value of 10 kΩ·cm 2 , and the simulation results show that under the condition of electrode stimulation, the conduction speed range of the action potential of the nerve fiber is 50 m / s to 80 m / s, and the attenuation rate in different tissue media during the conduction process is 2 mV per millimeter.

[0017] In the three-dimensional electric field coupling modeling method for analgesia provided by the present invention, it may further have the following characteristics: It further includes the following steps: S4, by constructing a dynamically monitored human skin impedance model, optimizing the electrode contact state and electric field distribution in real time to ensure the accuracy of stimulation.

[0018] In the three-dimensional electric field coupling modeling method for analgesia provided by the present invention, it may further have the following characteristics: Among them, step S4 further includes the following sub-steps: S4-1, based on the formula calculate the skin impedance, where R epidermis is the epidermal layer resistance, with a value of 1000 - 1500 Ω; X epidermis is the epidermal layer reactance, with a value of 200 - 500 Ω; ω is the angular frequency, with a value of 2π×1000 Hz; C epidermis is the epidermal layer capacitance, with a value of 10 μF / cm 2 ; S4-2, through a closed-loop feedback system, dynamically monitor the dynamic changes of the skin impedance, and dynamically adjust the electrode pressure and contact area to ensure the stability of the electric field intensity; S4-3, combined with the feedback regulation mechanism, optimize the electric field distribution within the impedance change range, and significantly improve the electrode contact reliability and the accuracy of the stimulation effect.

[0019] In the three-dimensional electric field coupling modeling method for analgesia provided by the present invention, it may further have the following characteristics: It further includes the following steps: S5, combining the electrophysiological characteristics of the nerve fiber and the impedance parameters of the human skin impedance model, dynamically optimize the electrical stimulation parameters and the signal conduction path.

[0020] In the three-dimensional electric field coupling modeling method for analgesia provided by the present invention, it may also have the following characteristics: In step S5, the electrical stimulation parameters are a voltage of 1 to 1.5 V and a pulse frequency of 20 to 100 Hz, so as to ensure the stable response of nerve fibers below the activation threshold. Based on the impedance change of the human skin impedance model, the electrical stimulation intensity and duration are dynamically adjusted to adapt to individual needs and environmental changes. The impedance change of the human skin impedance model is 1000 to 1500 Ω. For high-gradient regions, by optimizing the electric field conduction path, the excitatory signal of nerve fibers can be efficiently transmitted to the target region within 5 to 10 ms, significantly improving the rapidity and accuracy of the analgesic effect.

[0021] Functions and effects of the invention

[0022] According to a three-dimensional electric field coupling modeling method for analgesia involved in the present invention, through a three-dimensional bionic electric potential model and a dynamic feedback regulation mechanism, high-precision optimization of the electric field distribution is achieved, which can effectively cope with the complexity brought by different physiological tissues and individual differences, and provide a more accurate and stable solution in the treatment of chronic pain.

[0023] Combined with finite element analysis and nerve fiber simulation technology, it can dynamically optimize the electrode layout and electrical stimulation parameters, ensure the efficient transmission of nerve fiber action potentials and the precise inhibition of pain signals, and improve the immediacy and long-term effectiveness of the treatment effect.

[0024] By real-time adjusting the electric field intensity and distribution range, the present invention significantly reduces the discomfort caused by uneven electric field distribution or improper parameter setting in traditional electrical stimulation technology, and enhances the patient's treatment experience and safety.

[0025] The present invention is widely applicable to the clinical treatment and home rehabilitation scenarios of chronic pain patients, effectively solving the problems of uneven electric field control, non-persistent stimulation effect, and insufficient personalization in the existing technology, providing a precise, efficient, and reliable technical solution for non-invasive analgesic treatment, and is particularly suitable for the precise treatment of chronic pain. Brief description of the drawings

[0026] Figure 1 is the flowchart of three-dimensional electric field coupling modeling in the embodiment of the present invention; and

[0027] Figure 2 is the simulation process of nerve fiber action potential conduction in the embodiment of the present invention. Detailed implementation manners

[0028] In order to make the technical means, creative features, achieved purposes, and functions of the present invention easy to understand, the following embodiments will specifically describe a three-dimensional electric field coupling modeling method for analgesia of the present invention in conjunction with the drawings.

[0029] Figure 1 It is a flowchart of three-dimensional electric field coupling modeling in the embodiments of the present invention.

[0030] As Figure 1 shown, the three-dimensional electric field coupling modeling method for analgesia in this embodiment specifically includes the following steps:

[0031] S1. Construct a three-dimensional bionic electric potential model. Among them, the three-dimensional bionic electric potential model is a multi-layer bionic tissue model including skin, fat, muscle, nerve and blood vessels. The electrophysiological properties of each layer of tissue are characterized by different dielectric constants and conductivities. The dielectric constant is ε r = 20 - 1500, and the conductivity is σ = 0.01 - 0.2 S / m. The specific conductivity depends on the tissue type.

[0032] Based on Gauss's law and Maxwell's equations, by applying a voltage to the three-dimensional bionic electric potential model using a simulation electrode, the dielectric constants and conductivities of multi-layer physiological tissues are accurately simulated, so as to achieve the accurate calculation of the electric field strength and current density distribution.

[0033] When the simulation electrode applies a voltage, how the electric field propagates in these tissues, and according to the different tissue conductivities and resistance values, the distribution of the electric field strength and current density is calculated.

[0034] The material of the simulation electrode is silver / silver chloride (Ag / AgCl) with a diameter of 2 cm and excellent conductivity. Combined with a conductive gel as the medium to maintain the long-term stability of the contact impedance, and the conductivity of the conductive gel ≥ 1 S / m.

[0035] Control the shape of the simulation electrode to be circular or oval, with the size range of diameter 1 - 3 cm, the spacing of the simulation electrodes is 5 - 10 mm, the surface contact resistance is set to 500 Ω, and the best configuration is selected to achieve the uniform distribution of the electric field in the optimized target area and good electrode contact stability.

[0036] Stably maintain the current density of the simulation electrode at 0.05 - 0.1 A / m 2 , and the contact stability reaches more than 99%.

[0037] S2. Optimize the electrode excitation conditions, and through the accurate calculation of the electric field strength and current density distribution, ensure the uniformity and stability of the electric field coverage, and obtain a uniform and stable electric field distribution result.

[0038] Among them, the electrode excitation conditions include the electrode spacing and the surface contact resistance. The electrode spacing is 5 - 10 mm, and the surface contact resistance ≤ 500 Ω.

[0039] In this embodiment, the electrode spacing is set to 5 mm, the contact resistance of the electrode surface is 500 Ω, and the calculation formulas for the electric field strength (E) and current density (J) are as follows:

[0040]

[0041] J = σE

[0042] The electrode voltage is set to 1 V, and the maximum electric field strength value is 15 V / m. The simulation results show that the electric field strength is uniformly distributed within the target area.

[0043] Step S2 specifically includes the following sub-steps:

[0044] S2-1: Through the mesh refinement technique, comprehensively characterize the distribution characteristics of the high-gradient electric field in complex physiological structures, obtain the variation law of the electric field in the simulated identified high-gradient region, and the mesh element size in the mesh refinement technique is ≤ 0.01 mm.

[0045] The numerical simulation of the electric field distribution is based on the finite element analysis technique, and the specific steps include:

[0046] (1) Define the geometric boundary conditions of the three-dimensional bionic electric potential model, and the model size is 10 mm × 10 mm × 5 mm.

[0047] (2) Set the electrode positions and voltage source parameters, and the electrode voltage range is set from 0.5 V to 1.5 V.

[0048] (3) Use the refined mesh to calculate the high-gradient region, the minimum size of the mesh element is 0.01 mm, and the variation range of the simulated electric field strength is from 0 V / m to 20 V / m to improve the accuracy of the electric field distribution simulation.

[0049] The time-varying equation of the electric field is as follows:

[0050]

[0051] Among them, D is the electric displacement vector, H is the magnetic field strength, and J is the current density. The simulation results show that at the electrode contact point, the current density is 0.05 A / m 2 .

[0052] S2-2: Based on the variation law of the electric field in the simulated identified high-gradient region, dynamically optimize the electrode positions and voltage source parameters of the simulated electrodes, adjust the electrode layout scheme of the simulated electrodes, and conduct a detailed simulation on the three-dimensional bionic electric potential model to obtain the simulation results, thereby maximizing the uniformity of the electric field distribution in the three-dimensional bionic electric potential model.

[0053] Specifically, in the present invention, through finite element analysis technology, a detailed simulation of the subcutaneous electric field distribution is carried out. By establishing a high-precision multi-layer bionic tissue model, the system can capture the propagation process of the electric field in different tissues, especially in high-gradient regions, where refined mesh processing is performed. This simulation helps to evaluate the effects of electrode position, voltage magnitude, and tissue electrical properties on the electric field distribution. During the simulation, the electrode spacing, voltage source parameters, and electrical stimulation frequency are optimized. The specific results are as follows:

[0054] Electrode spacing: Testing spacings of 5 mm, 7 mm, and 10 mm found that when the spacing was 5 mm, the electric field uniformity in the target area increased from the traditional 91% to 93%.

[0055] Voltage source parameters: When the applied voltage was 1.2 V, the electric field strength in the target area stabilized at 0.2 - 0.35 V / m, meeting the requirements for nerve fiber activation.

[0056] Frequency setting: At a pulse frequency of 50 Hz, the conduction speed of the nerve fiber action potential increased from the traditional 62 m / s to 67 m / s.

[0057] Simulation results:

[0058] Electric field strength distribution: Under the optimized configuration, the amplitude of the electric field fluctuation in the target area decreased from ±8% to ±4%, and the electric field strength uniformity was significantly improved.

[0059] Nerve fiber excitation efficiency: The response threshold of the excitation function decreased from 0.2 V / m to 0.18 V / m, and the conduction speed of the action potential increased by 5 m / s.

[0060] Improvement in pain score: Under the optimized configuration, the improvement amplitude of the VAS score increased slightly from 5% to 7%.

[0061] S2-3, based on the above simulation results, further adjust the current density distribution of the simulation electrodes to reduce the interference of the electric field non-uniformity on the nerve fiber response, thereby improving the accuracy and efficacy of electrical stimulation, and finally establishing a high-precision three-dimensional bionic electric potential model.

[0062] S3, in combination with the nerve physiology model, input the electric field distribution results into the action potential conduction simulation module of the nerve fiber, and optimize the electrical stimulation parameters by dynamically simulating the electrophysiological responses of the nerve fiber to different electrical stimulation intensities.

[0063] Figure 2 This is the simulation process of the nerve fiber action potential conduction in the embodiment of the present invention.

[0064] As Figure 2 shown, it demonstrates the nerve response process under simulated electrical stimulation by combining the multi-compartment cable model and finite element analysis.

[0065] The system integrates a multi-compartment cable model to simulate the action potential conduction process of nerve fibers. By regulating the voltage applied by the electrodes, the transmembrane potential of the nerve fibers will change. The system evaluates the excitation threshold and conduction velocity of the nerve fibers under different electrical stimulation intensities through finite element analysis, and finally realizes the precise regulation of pain signal conduction.

[0066] The simulation results show that when the electric field strength reaches 0.1 V / m, the action potential of the nerve fiber can be excited, and the excitation conduction velocity is between 5 ms and 10 ms.

[0067] Step S3 specifically includes the following sub-steps:

[0068] S3-1, set the transmembrane capacitance of the nerve fiber to 1 μF / cm 2 , the activation threshold voltage is 0.5 V, the initial transmembrane potential is -70 mV, and simulate the action potential conduction response of the nerve fiber under the electric field strength of 0.1 - 0.5 V / m.

[0069] The activation threshold of the nerve fiber is calculated based on the stimulus intensity (I stim ), and the electrophysiological characteristics of the nerve fiber. The excitation threshold optimization formula is:

[0070]

[0071] Among them, σ takes the value of 0.05 S / m, d is the distance between the skin and the nerve fiber, set to 2 mm, V0 is the applied voltage, the range is 1 - 1.5 V, V threshold is the activation threshold voltage of the nerve fiber, taking the value of 0.5 V. Through iterative optimization, ensure that the nerve fiber is effectively activated at the threshold voltage.

[0072] S3-2, quantify the conduction velocity of the action potential of the nerve fiber, and analyze its dynamic stability under different physiological conditions through simulation. The conduction velocity is 50 - 80 m / s.

[0073] The change of the transmembrane potential of the nerve fiber is described by the following equation:

[0074]

[0075] Among them, C m is the membrane capacitance, taking the value of 1 μF / cm 2 ; V m is the transmembrane potential, the initial voltage is -70 mV, and the maximum action potential is 30 mV; I m is the membrane current, R m is the membrane resistance, taking the value of 10 kΩ·cm 2。The simulation results show that under the condition of electrode stimulation, the conduction velocity range of the action potential of nerve fibers is from 50 m / s to 80 m / s, and the attenuation rate in different tissue media during the conduction process is 2 mV per millimeter.

[0076] S3-3, by adjusting the electric stimulation intensity and frequency, optimizing the transmembrane potential change process of nerve fibers, significantly improving the efficiency and accuracy of electric stimulation, and optimizing the electric stimulation parameters.

[0077] S4, by constructing a dynamic monitoring human skin impedance model, optimizing the electrode contact state and electric field distribution in real time to ensure the accuracy of stimulation.

[0078] Specifically, the present invention monitors the state of the electrode in contact with the skin in real time by establishing a skin impedance model. Since the skin conductivity is affected by factors such as pressure, temperature, and humidity, the system adopts a dynamic feedback mechanism to adjust the electric stimulation parameters to ensure the stability and accuracy of the electric field distribution. The impedance feedback mechanism can not only dynamically adjust the output current and voltage, but also reduce errors and ensure the long-term effectiveness of treatment.

[0079] Step S4 specifically includes the following sub-steps:

[0080] S4-1, based on the formula

[0081]

[0082] calculate the skin impedance, where R epidermis is the epidermal resistance, with a value of 1000 - 1500 Ω; X epidermis is the epidermal reactance, with a value of 200 - 500 Ω; ω is the angular frequency, with a value of 2π×1000 Hz; C epidermis is the epidermal capacitance, with a value of 10 μF / cm 2 . This model can realize the real-time monitoring and feedback regulation of skin impedance changes, ensuring the accuracy and stability of the electric field distribution.

[0083] S4-2, through a closed-loop feedback system, monitor the dynamic changes of skin impedance in real time, and dynamically adjust the electrode pressure and contact area to ensure the stability of the electric field intensity.

[0084] S4-3, combined with the feedback regulation mechanism, optimize the electric field distribution within the impedance change range, significantly improving the electrode contact reliability and the accuracy of the stimulation effect.

[0085] S5, combined with the electrophysiological characteristics of nerve fibers and the impedance parameters of the human skin impedance model, dynamically optimize the electric stimulation parameters and signal conduction path.

[0086] Specifically, after completing the simulation of the initial electric field distribution and the simulation of nerve fiber conduction, the system continuously optimizes the intensity, frequency, and duration of the electrical stimulation according to the skin impedance feedback. Through the real-time monitoring of the skin impedance change, the feedback system can dynamically adjust the electrical stimulation parameters to ensure a stable and accurate response of the nerve fibers, thereby improving the effectiveness of pain regulation.

[0087] Among them, the electrical stimulation parameters are a voltage of 1 to 1.5 V and a pulse frequency of 20 to 100 Hz, so as to ensure a stable response of the nerve fibers below the activation threshold.

[0088] Based on the impedance change of the human skin impedance model, the electrical stimulation intensity and duration are dynamically adjusted to adapt to individual needs and environmental changes. The impedance change of the human skin impedance model is 1000 to 1500 Ω.

[0089] For high-gradient regions, by optimizing the electric field conduction path, the excitatory signal of the nerve fibers can be efficiently transmitted to the target region within 5 to 10 ms, significantly improving the rapidity and accuracy of the analgesic effect.

[0090] Functions and effects of the embodiments

[0091] According to a three-dimensional electric field coupling modeling method for analgesia involved in the present invention, through a three-dimensional bionic electric potential model and a dynamic feedback regulation mechanism, high-precision optimization of the electric field distribution is achieved, which can effectively cope with the complexity brought by different physiological tissues and individual differences, and provide a more accurate and stable solution in the treatment of chronic pain.

[0092] Combining finite element analysis and nerve fiber simulation technology can dynamically optimize the electrode layout and electrical stimulation parameters to ensure the efficient transmission of nerve fiber action potentials and the precise inhibition of pain signals, improving the immediacy and long-term effectiveness of the treatment effect.

[0093] By real-time adjusting the electric field intensity and distribution range, the present invention significantly reduces the discomfort caused by uneven electric field distribution or improper parameter setting in traditional electrical stimulation technology, enhancing the patient's treatment experience and safety.

[0094] The present invention is widely applicable to the clinical treatment and home rehabilitation scenarios of chronic pain patients, effectively solving the problems of uneven electric field control, non-sustained stimulation effect, and insufficient personalization in the existing technology, and providing a precise, efficient, and reliable technical solution for non-invasive analgesic treatment, especially suitable for the precise treatment of chronic pain.

[0095] The present invention realizes the precise control of the electric field distribution and the efficient adjustment of personalized analgesia parameters by constructing a multi-layer physiological tissue bionic model and a real-time dynamic optimization mechanism. The device uses finite element analysis technology and combines it with a simulation model of the action potential conduction of nerve fibers to dynamically simulate the propagation law of the electric field in multi-layer tissues and the response characteristics of nerve fibers. The real-time feedback mechanism adjusts the stimulation parameters (frequency, amplitude, and pulse width) according to the electric field simulation results and the personalized needs of the patient to ensure the stability of the electric field distribution and the persistence of the treatment effect.

[0096] The present invention realizes the precise regulation of pain signals by combining finite element analysis and a skin impedance feedback mechanism. This system can be widely applied to the non-invasive treatment of chronic pain, especially suitable for the remote regulation of low back pain. Through electrical stimulation at the ankle, the present invention avoids direct intervention in the lumbar lesions, not only improving the safety of the treatment but also significantly reducing the pain of the patient.

[0097] The present invention realizes the real-time monitoring and feedback regulation of skin impedance changes by constructing a human skin impedance model to ensure the accuracy and stability of the electric field distribution.

[0098] The present invention introduces a multi-compartment cable model in the simulation. Through precise dynamic simulation, it further improves the efficiency of nerve fiber activation and reduces the risk of misstimulation in non-target areas.

[0099] When the skin electrical properties (electrical impedance) of the patient fluctuate due to changes in humidity, temperature, or contact state, the present invention can optimize the uniformity of the electric field and the coverage effect of the target area by real-time regulating the electrode spacing, excitation voltage, and stimulation intensity.

[0100] Those skilled in the art should understand that the present invention is not limited by the above embodiments. What is described in the above embodiments and the specification only illustrates the principle of the present invention. Without departing from the spirit and scope of the present invention, the present invention will have various changes and improvements, and these changes and improvements all fall within the scope of the present invention claimed. The scope of protection claimed by the present invention is defined by the appended claims and their equivalents.

Claims

1. A three-dimensional electric field coupling modeling method for analgesia, characterized in that: The specific steps include: S1, constructing a three-dimensional bionic potential model, based on Gauss's law and Maxwell's equations, by using simulated electrodes to apply voltage to the three-dimensional bionic potential model, accurately simulating the dielectric constant and conductivity of multi-layer physiological tissue, thereby achieving accurate calculation of electric field intensity and current density distribution; S2, optimizing the electrode excitation conditions, and ensuring the uniformity and stability of the electric field coverage through accurate calculation of the electric field strength and current density distribution, so as to obtain a uniform and stable electric field distribution result; S3, combined with the neurophysiological model, inputs the electric field distribution results into the action potential conduction simulation module of the nerve fiber, optimizes the electrical stimulation parameters by dynamically simulating the electrophysiological response of the nerve fiber to different electrical stimulation intensities, and finally realizes the precise regulation of pain signal conduction. The three-dimensional bionic potential model is a multi-layer bionic tissue model including skin, fat, muscle, nerve and blood vessel, and the dielectric constant is ε r =20~1500, the conductivity is σ=0.01~0.2S / m, the electrode excitation conditions include electrode spacing and surface contact resistance, the electrode spacing is 5~10mm, and the surface contact resistance is ≤500Ω.

2. The three-dimensional electric field coupling modeling method for analgesia according to claim 1, characterized in that: in, In step S1, the material of the simulated electrode is silver / silver chloride Ag / AgCl with excellent conductivity, combined with conductive gel as a medium to maintain the long-term stability of the contact impedance, and the conductivity of the conductive gel is ≥1S / m. The shape of the simulated electrode is controlled to be circular or elliptical, with a size range of 1 to 3 cm in diameter and a spacing of 5 to 10 mm, so as to achieve uniform distribution of the electric field in the optimized target area. The current density of the simulated electrode is stably maintained at 0.05-0.1 A / m2, and the contact stability reaches more than 99%.

3. The three-dimensional electric field coupling modeling method for analgesia according to claim 1, characterized in that: in, Step S2 also includes the following sub-steps: S2-1, through the grid refinement technology, the distribution characteristics of high-gradient electric fields in complex physiological structures are fully characterized, and the electric field variation law of high-gradient areas is obtained by simulation identification, and the grid unit size in the grid refinement technology is ≤0.01mm; S2-2, based on the simulation to identify the electric field variation law of the high gradient area, dynamically optimize the electrode position and voltage source parameters of the simulated electrode, adjust the electrode arrangement scheme of the simulated electrode, and simulate the three-dimensional bionic potential model in detail to obtain simulation results, thereby maximizing the uniformity of the electric field distribution in the three-dimensional bionic potential model, the voltage range is 0.5 to 1.5 V, and the electric field uniformity is ≥ 93%; S2-3, based on the simulation results, further adjust the current density distribution of the simulated electrode to reduce the interference of electric field non-uniformity on the response of nerve fibers, thereby improving the accuracy and efficacy of electrical stimulation, and finally establish the high-precision three-dimensional bionic potential model.

4. The three-dimensional electric field coupling modeling method for analgesia according to claim 1, characterized in that: in, Step S3 also includes the following sub-steps: S3-1, setting the transmembrane capacitance of the nerve fiber to 1 μF / cm2, the activation threshold voltage to 0.5V, and the initial transmembrane potential to -70mV, simulating the action potential conduction response of the nerve fiber under an electric field strength of 0.1 to 0.5V / m; S3-2, simulating the transmembrane potential change process of nerve fibers, quantifying the conduction velocity of the action potential of the nerve fibers, and combining simulation to analyze its dynamic stability under different physiological conditions, the conduction velocity is 50-80 m / s; S3-3, by adjusting the intensity and frequency of electrical stimulation, optimize the transmembrane potential change process of nerve fibers, significantly improve the efficiency and accuracy of electrical stimulation, and optimize the electrical stimulation parameters.

5. The three-dimensional electric field coupling modeling method for analgesia according to claim 1, characterized in that: in, In step S3-1, the activation threshold voltage is calculated based on the stimulus intensity (I stim ) and the electrophysiological characteristics of nerve fibers, the excitation threshold optimization formula is: Where, σ is set to 0.05S / m, d is the distance between the skin and the nerve fiber, which is set to 2mm, V0 is the applied voltage, ranging from 1 to 1.5V, and V threshold is the activation threshold voltage of the nerve fiber, which is 0.5 V. Through iterative optimization, it is ensured that the nerve fiber is effectively activated at the threshold voltage.

6. The three-dimensional electric field coupling modeling method for analgesia according to claim 1, characterized in that: in, In step S3-2, the change in transmembrane potential of the nerve fiber is described by the following equation: Among them, C m is the membrane capacitance, which is 1μF / cm 2 ; V m is the transmembrane potential, the initial voltage is -70mV, and the maximum action potential is 30mV; I m is the membrane current, R m is the membrane resistance, which is 10 kΩ·cm 2 ,The simulation results show that under electrode stimulation conditions, the conduction velocity of the action potential of ,nerve fibers ranges from 50m / s to 80m / s, and the attenuation rate in different tissue media during ,conduction process is 2mV per millimeter.

7. The three-dimensional electric field coupling modeling method for analgesia according to claim 1, characterized in that: The following steps are also included: S4, by building a dynamically monitored human skin impedance model, optimizes the electrode contact status and electric field distribution in real time to ensure the accuracy of stimulation.

8. The three-dimensional electric field coupling modeling method for analgesia according to claim 7, characterized in that: in, Step S4 also includes the following sub-steps: S4-1, based on formula Calculate skin impedance, where R epidermis is the skin layer resistance, ranging from 1000 to 1500Ω; X epidermis is the skin layer reactance, which is 200~500Ω; ω is the angular frequency, which is 2π×1000Hz; C epidermis is the epidermal capacitance, with a value of 10μF / cm 2 ; S4-2, through the closed-loop feedback system, the dynamic changes of skin impedance are monitored in real time, and the electrode pressure and contact area are dynamically adjusted to ensure the stability of the electric field strength; S4-3, combined with the feedback control mechanism, optimizes the electric field distribution within the impedance change range, significantly improving the reliability of electrode contact and the accuracy of stimulation effect.

9. The three-dimensional electric field coupling modeling method for analgesia according to claim 8, characterized in that: The following steps are also included: S5, dynamically optimizing the electrical stimulation parameters and signal conduction path by combining the electrophysiological characteristics of the nerve fibers with the impedance parameters of the human skin impedance model.

10. The three-dimensional electric field coupling modeling method for analgesia according to claim 9, characterized in that: in, In step S5, the electrical stimulation parameters are voltage 1 to 1.5 V and pulse frequency 20 to 100 Hz, so as to ensure that the nerve fibers respond stably under the activation threshold. Based on the impedance change of the human skin impedance model, the intensity and duration of electrical stimulation are dynamically adjusted to adapt to individual needs and environmental changes. The impedance change of the human skin impedance model is 1000-1500Ω. For high-gradient areas, by optimizing the electric field conduction path, the excitation signals of the nerve fibers can be efficiently transmitted to the target area within 5 to 10 ms, significantly improving the speed and accuracy of the analgesic effect.

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