Electrical field stimulation closed-loop control method and device based on electrical impedance imaging

Abstract

The application discloses an electric field stimulation closed-loop control method and device based on electrical impedance imaging. The method comprises the following steps: obtaining measured voltage change information, coupling the information with detection images and user breathing data to generate a digital twin model, obtaining a sensitive field corresponding to each excitation measurement combination according to the digital twin model and a constant excitation current, performing differential imaging to obtain a reconstructed image, performing convex optimization on the reconstructed image after assigning an absolute conductivity to obtain target optimization parameters, and generating corresponding control instructions according to the target optimization parameters and sending the instructions to an electric stimulation unit. The electric field stimulation closed-loop control method based on electrical impedance imaging optimizes initial control parameters by constructing a digital twin model and combining image processing, thereby obtaining accurate target optimization parameters, improving the application effect of electric field stimulation control through closed-loop optimization, and greatly improving the accuracy of electric field stimulation control.

Description

Technical Field

[0001] This invention relates to the field of intelligent control technology for electric field stimulation, and in particular to a closed-loop control method and device for electric field stimulation based on electrical impedance imaging. Background Technology

[0002] Existing technologies employ low-intensity alternating electric fields of specific frequencies to interfere with tumor cell division, thereby inhibiting tumor growth. The principle is to disrupt microtubule assembly and chromosome separation within tumor cells during the mitotic phase, inhibiting tumor cell mitosis and thus suppressing their growth. Normal cells, due to their slower division, are less affected. However, in practical applications, the distribution of the electric field generated in vivo is a key factor affecting its inhibitory effect. Nevertheless, existing methods for controlling the generation of electric field stimulation suffer from insufficient precision. Summary of the Invention

[0003] This invention provides a closed-loop control method and apparatus for electric field stimulation based on electrical impedance imaging, aiming to solve the problem of insufficient accuracy in existing control methods for generating electric field stimulation.

[0004] In a first aspect, embodiments of the present invention provide a closed-loop control method for electric field stimulation based on electrical impedance imaging, wherein the method is applied in a control terminal, the control terminal is communicatively connected to an excitation acquisition unit and an electric stimulation unit to achieve data information transmission, the excitation acquisition unit and the electric stimulation unit are respectively electrically connected to an electrode array, the electrode array being worn at the stimulation site, and the method includes:

[0005] The voltage change information obtained by the excitation acquisition unit is acquired based on the input initial control parameters.

[0006] The voltage change information and user breathing data are coupled based on the input detection image to obtain the corresponding digital twin model;

[0007] The sensitive fields corresponding to each excitation measurement combination are obtained based on the digital twin model and the excitation constant current in the initial control parameters.

[0008] Differential imaging is performed on the sensitive field based on the user's breathing data and the digital twin model to obtain the corresponding reconstructed image;

[0009] The reconstructed image is assigned an absolute conductivity value based on the digital twin model to obtain the corresponding absolute conductivity assignment result;

[0010] The initial control parameters are convexly optimized according to the preset convex optimization rules and the absolute conductivity assignment results to obtain the corresponding target optimization parameters;

[0011] Based on the target optimization parameters, corresponding control commands are generated and sent to the electrical stimulation unit to control the electrode array.

[0012] Secondly, embodiments of the present invention also provide a closed-loop control device for electric field stimulation based on electrical impedance imaging, wherein the device is configured in a control terminal, the control terminal is communicatively connected to an excitation acquisition unit and an electrical stimulation unit to realize data information transmission, the excitation acquisition unit and the electrical stimulation unit are respectively electrically connected to an electrode array, the electrode array is worn on the stimulation site, and the device is used to execute the closed-loop control method for electric field stimulation based on electrical impedance imaging as described in the first aspect above, the device comprising:

[0013] A voltage change information acquisition unit is used to acquire voltage change information measured by the excitation acquisition unit based on the input initial control parameters.

[0014] The coupling unit is used to couple the voltage change information and the user's breathing data according to the input detection image to obtain the corresponding digital twin model;

[0015] The sensitive field acquisition unit is used to acquire the sensitive field corresponding to each excitation measurement combination based on the digital twin model and the excitation constant current in the initial control parameters.

[0016] The image reconstruction acquisition unit is used to perform differential imaging on the sensitive field based on the user's breathing data and the digital twin model to obtain the corresponding reconstructed image;

[0017] The assignment unit is used to assign an absolute conductivity value to the reconstructed image according to the digital twin model, and obtain the corresponding absolute conductivity assignment result;

[0018] An optimization unit is used to perform convex optimization on the initial control parameters according to a preset convex optimization rule and the absolute conductivity assignment result, so as to obtain the corresponding target optimization parameters.

[0019] A control command sending unit is used to generate corresponding control commands based on the target optimization parameters and send them to the electrical stimulation unit so as to control the electrode array through the electrical stimulation unit.

[0020] Thirdly, embodiments of the present invention also provide a computer device, wherein the device includes a processor, a communication interface, a memory, and a communication bus, wherein the processor, the communication interface, and the memory communicate with each other through the communication bus;

[0021] Memory, used to store computer programs;

[0022] When the processor executes the program stored in the memory, it implements the steps of the electric field stimulation closed-loop control method based on electrical impedance imaging as described in the first aspect above.

[0023] Fourthly, embodiments of the present invention also provide a computer-readable storage medium having a computer program stored thereon, wherein the computer program, when executed by a processor, implements the steps of the electric field stimulation closed-loop control method based on electrical impedance imaging as described in the first aspect above.

[0024] This invention provides a closed-loop control method and apparatus for electric field stimulation based on electrical impedance imaging. The method includes: acquiring measured voltage change information and coupling it with detected images and user respiratory data to generate a digital twin model; acquiring the sensitive fields corresponding to each excitation measurement combination based on the digital twin model and the excitation constant current, and performing differential imaging to obtain reconstructed images; assigning absolute conductivity values ​​to the reconstructed images and performing convex optimization to obtain target optimization parameters; and generating corresponding control commands based on the target optimization parameters and sending them to the electrical stimulation unit. This closed-loop control method for electric field stimulation based on electrical impedance imaging optimizes initial control parameters by constructing a digital twin model and combining image processing, thereby obtaining accurate target optimization parameters. This closed-loop optimization improves the application effect of electric field stimulation control and significantly enhances the accuracy of electric field stimulation control. Attached Figure Description

[0025] To more clearly illustrate the technical solutions of the embodiments of the present invention, the drawings used in the following description of the embodiments will be briefly introduced. Obviously, the drawings described below are some embodiments of the present invention. For those skilled in the art, other drawings can be obtained based on these drawings without creative effort.

[0026] Figure 1 A flowchart of the closed-loop control method for electric field stimulation based on electrical impedance imaging provided in an embodiment of the present invention;

[0027] Figure 2 A schematic diagram illustrating an application scenario of the closed-loop control method for electric field stimulation based on electrical impedance imaging provided in this embodiment of the invention;

[0028] Figure 3 A schematic block diagram of an electric field stimulation closed-loop control device based on electrical impedance imaging provided in an embodiment of the present invention;

[0029] Figure 4 This is a schematic block diagram of a computer device provided in an embodiment of the present invention. Detailed Implementation

[0030] The technical solutions of the embodiments of the present invention will be clearly and completely described below with reference to the accompanying drawings. Obviously, the described embodiments are only some, not all, of the embodiments of the present invention. Based on the embodiments of the present invention, all other embodiments obtained by those skilled in the art without creative effort are within the scope of protection of the present invention.

[0031] It should be understood that, when used in this specification and the appended claims, the terms "comprising" and "including" indicate the presence of the described features, integrals, steps, operations, elements and / or components, but do not exclude the presence or addition of one or more other features, integrals, steps, operations, elements, components and / or collections thereof.

[0032] It should also be understood that the terminology used in this specification is for the purpose of describing particular embodiments only and is not intended to limit the invention. As used in this specification and the appended claims, the singular forms “a,” “an,” and “the” are intended to include the plural forms unless the context clearly indicates otherwise.

[0033] It should also be further understood that the term "and / or" as used in this specification and the appended claims refers to any combination of one or more of the associated listed items and all possible combinations, and includes such combinations.

[0034] The embodiments of this invention provide a closed-loop control method for electric field stimulation based on electrical impedance imaging, such as... Figure 2As shown, this method is applied in a control terminal 10. The control terminal 10 is communicatively connected to the excitation acquisition unit 20 and the electrical stimulation unit 30 to transmit data information. The excitation acquisition unit 20 and the electrical stimulation unit 30 are electrically connected to the electrode array 40, which is worn on the stimulation site. This electric field stimulation closed-loop control method is executed by application software installed in the control terminal 10. The control terminal 10 is a terminal device used to acquire detection information, process it, and generate corresponding control commands, such as a desktop computer, laptop computer, tablet computer, or mobile phone. The excitation acquisition unit 20 is used to drive the electrode array to generate the current excitation required for measurement and to receive voltage measurement signals in real time. That is, after each excitation, the voltage signals of all electrode pairs in the electrode array 40 are acquired. The electrical stimulation unit 30 is used to generate the input current corresponding to the electric field stimulation according to the control command, that is, to generate a stable and safe current according to the target optimization parameters to drive the electrode array 40 to generate electric field stimulation. The electrode array 40 is used for voltage measurement and stimulation current injection. It adopts a three-layer electrode structure, with the middle layer aligned with the target stimulation area. Each layer contains 16 electrodes. Flexible electrodes are used to better fit the user's torso, thereby improving imaging and treatment effects. An electrode in the upper layer and an electrode in the lower layer are paired to form an electrode pair.

[0035] like Figure 1 As shown, the method includes steps S110 to S170.

[0036] S110. Obtain the voltage change information measured by the excitation acquisition unit based on the input initial control parameters.

[0037] First, the voltage change information measured by the excitation acquisition unit is obtained based on the input initial control parameters. The excitation acquisition unit can be controlled by the initial control parameters to output a corresponding current excitation to drive the electrode array to generate electrical stimulation. The real-time voltage measurement signal fed back by the electrode array is then acquired by the excitation acquisition unit, thereby measuring the voltage change information.

[0038] In a specific embodiment, step S110 includes the following sub-steps: generating an initial control command based on the initial control parameters and sending it to the excitation acquisition unit to obtain the initial state voltage measurement acquired by the excitation acquisition unit and calibrating the measurement signal to obtain calibration measurement information; generating an adjacent electrode sequential excitation command based on the initial control parameters and sending it to the excitation acquisition unit to obtain the voltage change measurement information obtained by the excitation acquisition unit during the complete breathing process; and combining the calibration measurement information with the voltage change measurement information to obtain the corresponding voltage change information.

[0039] Specifically, based on the excitation constant current set in the initial control parameters, a corresponding initial control command is generated and sent to the excitation acquisition unit. The current output to the electrode array at this time is the excitation constant current. This process involves initial state voltage measurement, which is then used for subsequent respiratory phase division. Specifically, voltage measurement signals during the user's breathing process can be acquired and calibrated in conjunction with the user's breathing process. The voltage measurement value at the end of expiration in the measurement signal is calibrated based on the user's expiration end time point, and the voltage measurement value at the end of inspiration in the measurement signal is calibrated based on the user's inspiratory end time point. The two calibrated voltage measurement values ​​are then obtained to acquire calibration measurement information.

[0040] Furthermore, based on the constant excitation current set in the initial control parameters, a sequential excitation command is generated for adjacent electrodes. The excitation acquisition unit then drives adjacent electrodes in the electrode array to sequentially undergo current excitation according to the received sequential excitation command. When one electrode (including the upper and lower electrodes at the same position) undergoes current excitation, the remaining electrodes undergo voltage measurement. After one measurement is completed, the next electrode adjacent to the electrode that generated the current excitation is driven to undergo current excitation, and the remaining electrodes undergo voltage measurement. This process is repeated until all electrodes have undergone current excitation once. By acquiring the voltage measurement information, the change in measured voltage during the user's complete breathing process can be obtained, i.e., the corresponding voltage change measurement information is obtained. For example, the current flowing into the electrodes can be switched sequentially, with 1mA flowing in each time, and the voltage of the remaining electrodes can be measured.

[0041] The obtained calibration measurement information is combined with the voltage change measurement information to obtain the voltage change information.

[0042] S120. The voltage change information and user breathing data are coupled according to the input detection image to obtain the corresponding digital twin model.

[0043] A digital twin model is constructed by coupling voltage change information and user breathing data based on the input detection images. Specifically, the detection images are CT scans of the user's lungs, including CT scans of the lungs at the end of inspiration and expiration. The detection images are preprocessed (including tissue segmentation, smoothing, and denoising) to construct a lung geometric model. Then, the static lung geometric model is transformed into a dynamic virtual breathing model using the mechanical information corresponding to the user's breathing data. Simultaneously, voltage change information obtained from in vitro measurements is coupled to obtain a digital twin model corresponding to the virtual breathing model.

[0044] Specifically, since there is a certain linear relationship between the breathing phase and the voltage change measurement information, the calibration measurement information in the voltage change information can be used as a label to segment the voltage change measurement information to obtain the average voltage measurement corresponding to a complete breathing phase. Specifically, based on the calibration measurement information as a label, the voltage change measurement information can be segmented to obtain the voltage change for each complete breathing process. Each complete breathing process includes the end of expiration of the previous breath to the end of expiration of the current breath; each complete breathing process can also be divided into two sub-processes: the end of expiration of the previous breath to the end of inhalation of the current breath, and the end of inhalation of the current breath to the end of expiration of the current breath. By obtaining the average voltage value at each moment for multiple complete breathing processes corresponding to the segmented voltage changes, the average voltage measurement corresponding to the complete breathing phase can be obtained. The average voltage measurement is then linearly fitted to the dynamic image of the virtual breathing model, or coupled using methods such as nonlinear regression, to construct a digital twin model.

[0045] S130. Obtain the sensitive field corresponding to each excitation measurement combination based on the digital twin model and the excitation constant current in the initial control parameters.

[0046] Furthermore, the FEM finite element method is used to calculate the sensitive field based on the digital twin model and the constant excitation current in the initial control parameters, thereby obtaining the sensitive field corresponding to each excitation measurement combination.

[0047] In a specific embodiment, step S130 includes the following sub-steps: dividing the digital twin model into meshes and constructing a corresponding stiffness matrix based on the mesh cells obtained from the division; calculating the corresponding potential distribution based on the excitation constant current and the stiffness matrix; and obtaining the sensitive fields corresponding to each excitation measurement combination and the potential distribution.

[0048] First, the model image at the computation time in the digital twin model is meshed, dividing the entire model image into a set of triangular elements. A stiffness matrix K is constructed, and for the e-th element, its stiffness matrix is:

[0049] (1);

[0050] Where, N e σ is the element shape function. e For unit conductivity, ▽N e The gradient of the shape function, which is a vector, is expressed as:

[0051] ;

[0052] (∇N e ) TThis involves a suitable conversion operation on the gradient, which is represented by a corresponding row vector:

[0053] .

[0054] Given the defined boundary current excitation conditions, when exciting any electrode pair, the excitation constant current is I. Based on the stiffness matrix K and the excitation constant current I, the potential distribution φ can be further calculated using the formula K×φ=I.

[0055] Further, the sensitive fields corresponding to each excitation measurement combination and potential distribution are obtained; under a certain excitation measurement combination, the sensitive fields of the excitation electrode pair (a, b) and the measurement electrode pair (m, n) are:

[0056] (2);

[0057] in, It is a vector, representing the potential direction corresponding to the location of a specific electrode. That is, the potential distribution located at the electrode pair (a, b) and The corresponding potential gradient, That is, the potential distribution located at the electrode pair (m, n) and The corresponding potential gradient.

[0058] S140. Differential imaging is performed on the sensitive field based on the user's breathing data and the digital twin model to obtain the corresponding reconstructed image.

[0059] Furthermore, differential imaging is performed on the sensitive field obtained in the above steps based on the user's breathing data and digital twin model to obtain the corresponding reconstructed image, which is also a conductivity change map.

[0060] In a specific embodiment, step S140 includes the following sub-steps: dividing the complete breathing stage according to the user's breathing data to obtain multiple corresponding breathing phases; coupling the breathing phases according to the digital twin model to generate conductivity images corresponding to each breathing phase; and reconstructing the conductivity images according to the sensitive field and the objective function to obtain the image corresponding to the minimum function value of the objective function as the reconstructed image.

[0061] The complete breathing stage is divided based on the user's breathing data to obtain multiple corresponding breathing phases. In other words, the user's complete breathing stage is divided into 10 breathing phases based on time, and each breathing phase corresponds to a breathing action process.

[0062] Furthermore, the respiratory phases are coupled according to the digital twin model to generate conductivity images corresponding to each respiratory phase. In other words, the conductivity images of each respiratory phase are generated by coupling the electrical and geometric characteristics of the digital twin model.

[0063] In a specific embodiment, the step of reconstructing the conductivity image based on the sensitive field and the target function to obtain the image corresponding to the minimum function value of the target function as the reconstructed image includes: obtaining the measured phase position corresponding to the average voltage measurement in the voltage change information based on the digital twin model; obtaining the conductivity labels of the phases adjacent to the measured phase position in the conductivity image based on the breathing phase; performing cross-gradient calculations on the conductivity labels of adjacent phases according to the cross-gradient coupling algorithm and the conductivity distribution corresponding to the conductivity image to obtain the gradient value corresponding to each conductivity label; inputting the conductivity distribution corresponding to the conductivity image, the voltage measurement value in the voltage change information, and the gradient value into the target function to calculate the corresponding function value; and reconstructing the conductivity image based on the change in the function value of the target function to obtain the image corresponding to the minimum function value of the target function as the reconstructed image.

[0064] Specifically, the time point of the average voltage measurement in the complete breathing stage can be determined based on the average voltage measurement in the voltage change information. Then, the breathing phase corresponding to the time point of the average voltage measurement can be determined based on the time point of the average voltage measurement. The determined breathing phase is then obtained as the measured phase position corresponding to the average voltage measurement.

[0065] Further, based on the measured phase position, the conductivity labels of the phases adjacent to the measured phase position in the conductivity image are obtained. For example, the conductivity labels of the phases adjacent to the measured phase position of the voltage measurement mean are σ. C1 and σ C2 .

[0066] Furthermore, based on the cross-gradient coupling algorithm and the conductivity distribution corresponding to the conductivity image, cross-gradient calculations are performed on each conductivity label. The imaging structure can be optimized based on the conductivity labels of two adjacent phases at the measured location. The cross-gradient method is used to couple the structural information of the conductivity labels. The cross-gradient coupling algorithm is expressed by the following formula:

[0067] (3);

[0068] Where, σ E For conductivity distribution, σ C The conductivity labels for adjacent phases (specifically σ) C1 or σ C2 Then, for each conductivity label, a gradient value can be obtained (specifically t(σ)).E ,σ C1 ) or t(σ E ,σ C1 )).

[0069] The conductivity distribution corresponding to the conductivity image, the voltage measurement value from the voltage change information, and the gradient value are input into the objective function to calculate the corresponding function value. The objective function can be expressed as:

[0070] (4);

[0071] Where F(σ) E The calculated conductivity distribution σ is the result of calculation. E The corresponding function values ​​are V, which is the measured voltage value, L, which is the Tikhonov regularization matrix, and α, β, and β2 are all coefficient values ​​set in the objective function.

[0072] The conductivity image is reconstructed based on the change in the function value of the objective function. For example, the reconstruction algorithm such as Tikohonov can be used to reconstruct the image, and the image with the minimum function value of the objective function among the reconstructed images is obtained as the corresponding reconstructed image.

[0073] S150. Assign absolute conductivity values ​​to the reconstructed image based on the digital twin model to obtain the corresponding absolute conductivity assignment results.

[0074] The absolute conductivity amplitude is calculated based on the obtained digital twin model to obtain the corresponding absolute conductivity assignment result.

[0075] In a specific embodiment, step S150 includes the following sub-steps: normalizing the reconstructed image to obtain a corresponding normalized image; and assigning an absolute conductivity value to the normalized image according to the digital twin model to obtain a corresponding absolute conductivity assignment result.

[0076] Specifically, the reconstructed image can be normalized to obtain a corresponding normalized image. The normalization process can be based on a normalization function, which can be used to calculate the normalized conductivity value of each pixel in the reconstructed image. The normalized values ​​are then integrated to obtain the corresponding normalized image.

[0077] Further, the normalized image is assigned an absolute conductivity value based on the digital twin model. This assignment can be done using the end-expiratory conductivity and end-inspiratory conductivity information from the digital twin model, with the following amplitude method:

[0078] (5);

[0079] Where, σ absolute (i) represents the absolute conductivity after assignment, a(i) is the linear coefficient, b(i) is the background conductivity (obtained based on the end-expiratory conductivity information and the end-inspiratory conductivity information), σ norm (i) represents the normalized conductivity value corresponding to the i-th pixel in the normalized image. The absolute conductivity value can be obtained by acquiring the absolute conductivity value for each pixel.

[0080] S160. Perform convex optimization on the initial control parameters according to the preset convex optimization rules and the absolute conductivity assignment result to obtain the corresponding target optimization parameters.

[0081] Furthermore, based on the convex optimization rules and the absolute conductivity assignment results, the initial control parameters are convex optimized to obtain the target optimized parameters corresponding to the initial control parameters.

[0082] In a specific embodiment, step S160 includes the following sub-steps: calculating the corresponding lead field matrix based on the electric field distribution of each given current vector in the absolute conductivity assignment result; and performing convex optimization on the initial control parameters based on the optimization function in the convex optimization rule and the lead field matrix to obtain the corresponding target optimization parameters.

[0083] Specifically, the corresponding lead field matrix can be calculated based on the electric field distribution of each given current vector in the absolute conductivity assignment result; the corresponding lead field matrix A can be calculated based on the absolute conductivity assignment result (i.e., the absolute conductivity assignment map). The electric field distribution of a given current vector s in the conductivity assignment result can be represented as e, and its specific calculation formula is as follows:

[0084] (6);

[0085] The absolute conductivity value σ obtained by solving the problem is... absolute This allows FEM to calculate the electric field distribution e generated under this distribution, given a current vector s. Then, when s and e are known quantities, the corresponding conduction field matrix A can be calculated.

[0086] Furthermore, based on the acquired lead field matrix, convex optimization is performed on the initial control parameters. The optimization objectives are the magnitude of the electrode injection current, the number of electrodes, and the selection of electrodes within the initial control parameters. The goal is to achieve the maximum electric field intensity and optimal focusing in the target stimulation region under the condition of minimum injection current. The optimization function configured in the convex optimization rules is as follows:

[0087] (7);

[0088] S is a given current vector, C is the component lead field matrix in lead field matrix A corresponding to the target stimulation region; λ is a coefficient set in the formula, arg is the average calculation, sum is the cumulative operation, and e0.25max is the electric field intensity at the maximum distance of one-quarter of the distance from the center point of the target stimulation region. The numerical value of the optimization function is obtained, and the initial parameters are iteratively optimized to maximize the value of the optimization function; the control parameter obtained when the value of the optimization function is maximized is used as the target optimization parameter.

[0089] S170. Generate corresponding control commands based on the target optimization parameters and send them to the electrical stimulation unit to control the electrode array through the electrical stimulation unit.

[0090] The corresponding control command is generated based on the target optimization parameters and sent to the electrostimulation unit. The target optimization parameters include the optimal electrode injection current, the number of electrodes, and the selection of electrodes. The electrostimulation unit then generates a corresponding output current based on the received control command and outputs it to the electrode matrix. The output current drives the electrode matrix to generate an electric field stimulation, thereby achieving control of the electrode matrix.

[0091] The closed-loop control method for electric field stimulation based on electrical impedance imaging disclosed in the above embodiments includes: acquiring measured voltage change information and coupling it with detection images and user respiratory data to generate a digital twin model; acquiring the sensitive field corresponding to each excitation measurement combination based on the digital twin model and the excitation constant current, and performing differential imaging to obtain a reconstructed image; assigning absolute conductivity values ​​to the reconstructed image and performing convex optimization to obtain target optimization parameters; and generating corresponding control commands based on the target optimization parameters and sending them to the electric stimulation unit. This closed-loop control method for electric field stimulation based on electrical impedance imaging optimizes initial control parameters by constructing a digital twin model and combining it with image processing, thereby obtaining accurate target optimization parameters. This improves the application effect of electric field stimulation control through closed-loop optimization, significantly enhancing the accuracy of electric field stimulation control.

[0092] This invention also provides a closed-loop control device for electric field stimulation based on electrical impedance imaging. This device can be configured in a control terminal and is used to execute any of the aforementioned embodiments of the closed-loop control method for electric field stimulation based on electrical impedance imaging. Specifically, please refer to... Figure 3 , Figure 3 This is a schematic block diagram of an electric field stimulation closed-loop control device based on electrical impedance imaging provided in an embodiment of the present invention.

[0093] like Figure 3As shown, the closed-loop control device 100 for electric field stimulation based on electrical impedance imaging includes a voltage change information acquisition unit 110, a coupling unit 120, a sensitive field acquisition unit 130, a reconstructed image acquisition unit 140, an assignment unit 150, an optimization unit 160, and a control command sending unit 170.

[0094] The voltage change information acquisition unit 110 is used to acquire the voltage change information measured by the excitation acquisition unit based on the input initial control parameters.

[0095] The coupling unit 120 is used to couple the voltage change information and the user's breathing data according to the input detection image to obtain a corresponding digital twin model;

[0096] Sensitive field acquisition unit 130 is used to acquire the sensitive field corresponding to each excitation measurement combination based on the digital twin model and the excitation constant current in the initial control parameters.

[0097] The reconstructed image acquisition unit 140 is used to perform differential imaging on the sensitive field based on the user's breathing data and the digital twin model to obtain the corresponding reconstructed image;

[0098] The assignment unit 150 is used to assign an absolute conductivity value to the reconstructed image according to the digital twin model, and obtain the corresponding absolute conductivity assignment result.

[0099] The optimization unit 160 is used to perform convex optimization on the initial control parameters according to the preset convex optimization rules and the absolute conductivity assignment result, so as to obtain the corresponding target optimization parameters.

[0100] The control command sending unit 170 is used to generate corresponding control commands based on the target optimization parameters and send them to the electrical stimulation unit so as to control the electrode array through the electrical stimulation unit.

[0101] The closed-loop control device for electric field stimulation based on electrical impedance imaging provided in this embodiment of the invention applies the aforementioned closed-loop control method for electric field stimulation based on electrical impedance imaging. It acquires measured voltage change information and couples it with detected images and user respiratory data to generate a digital twin model. Based on the digital twin model and the constant excitation current, it acquires the sensitive fields corresponding to each excitation measurement combination and performs differential imaging to obtain reconstructed images. After assigning absolute conductivity values ​​to the reconstructed images, it performs convex optimization to obtain target optimization parameters. Based on the target optimization parameters, it generates corresponding control commands and sends them to the electric stimulation unit. This closed-loop control method for electric field stimulation based on electrical impedance imaging optimizes initial control parameters by constructing a digital twin model and combining image processing, thereby obtaining accurate target optimization parameters. This closed-loop optimization improves the application effect of electric field stimulation control and significantly enhances the accuracy of electric field stimulation control.

[0102] The aforementioned closed-loop control device for electric field stimulation based on electrical impedance imaging can be implemented as a computer program, which can be used in, for example... Figure 4 It runs on the computer device shown.

[0103] Please see Figure 4 , Figure 4 This is a schematic block diagram of a computer device provided in an embodiment of the present invention. The computer device can be a control terminal used to execute a closed-loop control method for electric field stimulation based on electrical impedance imaging to acquire detection information and generate corresponding control commands after processing.

[0104] See Figure 4 The computer device 500 includes a processor 502, a memory, and a communication interface 505 connected via a communication bus 501. The memory may include a storage medium 503 and internal memory 504.

[0105] The storage medium 503 may store an operating system 5031 and a computer program 5032. When the computer program 5032 is executed, it enables the processor 502 to execute a closed-loop control method for electric field stimulation based on electrical impedance imaging. The storage medium 503 may be a volatile storage medium or a non-volatile storage medium.

[0106] The processor 502 provides computing and control capabilities to support the operation of the entire computer device 500.

[0107] The internal memory 504 provides an environment for the operation of the computer program 5032 in the storage medium 503. When the computer program 5032 is executed by the processor 502, the processor 502 can execute the closed-loop control method of electric field stimulation based on electrical impedance imaging.

[0108] This communication interface 505 is used for network communication, such as providing data transmission. Those skilled in the art will understand that... Figure 4 The structure shown is merely a block diagram of a portion of the structure related to the present invention and does not constitute a limitation on the computer device 500 to which the present invention is applied. The specific computer device 500 may include more or fewer components than shown in the figure, or combine certain components, or have different component arrangements.

[0109] The processor 502 is used to run the computer program 5032 stored in the memory to implement the corresponding functions in the above-mentioned closed-loop control method for electric field stimulation based on electrical impedance imaging.

[0110] Those skilled in the art will understand that Figure 4The embodiments of the computer device shown do not constitute a limitation on the specific configuration of the computer device. In other embodiments, the computer device may include more or fewer components than illustrated, or combine certain components, or have different component arrangements. For example, in some embodiments, the computer device may include only memory and a processor. In such embodiments, the structure and function of the memory and processor are different from those shown. Figure 4 The embodiments shown are consistent and will not be described again here.

[0111] It should be understood that, in this embodiment of the invention, the processor 502 may be a Central Processing Unit (CPU), but it may also be other general-purpose processors, digital signal processors (DSPs), microcontroller units (MCUs), application-specific integrated circuits (ASICs), field-programmable gate arrays (FPGAs), or other programmable logic devices, discrete gate or transistor logic devices, discrete hardware components, etc. The general-purpose processor may be a microprocessor or any conventional processor.

[0112] In another embodiment of the invention, a computer-readable storage medium is provided. This computer-readable storage medium may be volatile or non-volatile. The computer-readable storage medium stores a computer program, wherein when executed by a processor, the computer program implements the steps included in the above-described closed-loop control method for electric field stimulation based on electrical impedance imaging.

[0113] Those skilled in the art will readily understand that, for the sake of convenience and brevity, the specific working processes of the devices, apparatuses, and units described above can be referred to the corresponding processes in the foregoing method embodiments, and will not be repeated here. Those skilled in the art will recognize that the units and algorithm steps of the various examples described in conjunction with the embodiments disclosed herein can be implemented in electronic hardware, computer software, or a combination of both. To clearly illustrate the interchangeability of hardware and software, the composition and steps of each example have been generally described in terms of function in the foregoing description. Whether these functions are implemented in hardware or software depends on the specific application and design constraints of the technical solution. Those skilled in the art can use different methods to implement the described functions for each specific application, but such implementation should not be considered beyond the scope of this invention.

[0114] In the embodiments provided by this invention, it should be understood that the disclosed devices, apparatuses, and methods can be implemented in other ways. For example, the apparatus embodiments described above are merely illustrative. For instance, the division of units is only a logical functional division, and in actual implementation, there may be other division methods. Units with the same function may be grouped into one unit. For example, multiple units or components may be combined or integrated into another system, or some features may be ignored or not executed. In addition, the coupling or direct coupling or communication connection shown or discussed may be an indirect coupling or communication connection through some interfaces, devices, or units, or it may be an electrical, mechanical, or other form of connection.

[0115] The units described as separate components may or may not be physically separate. The components shown as units may or may not be physical units; that is, they may be located in one place or distributed across multiple network units. Some or all of the units can be selected to achieve the purpose of the embodiments of the present invention, depending on actual needs.

[0116] Furthermore, the functional units in the various embodiments of the present invention can be integrated into one processing unit, or each unit can exist physically separately, or two or more units can be integrated into one unit. The integrated unit can be implemented in hardware or as a software functional unit.

[0117] If the integrated unit is implemented as a software functional unit and sold or used as an independent product, it can be stored in a computer-readable storage medium. Based on this understanding, the technical solution of the present invention, in essence, or the part that contributes to the prior art, or all or part of the technical solution, can be embodied in the form of a software product. This computer software product is stored in a computer-readable storage medium and includes several instructions to cause a computer device (which may be a personal computer, server, or network device, etc.) to execute all or part of the steps of the methods described in the various embodiments of the present invention. The aforementioned computer-readable storage medium includes various media capable of storing program code, such as USB flash drives, portable hard drives, read-only memory (ROM), magnetic disks, or optical disks.

[0118] The above description is merely a specific embodiment of the present invention, but the scope of protection of the present invention is not limited thereto. Any person skilled in the art can easily conceive of various equivalent modifications or substitutions within the technical scope disclosed in the present invention, and these modifications or substitutions should all be covered within the scope of protection of the present invention. Therefore, the scope of protection of the present invention should be determined by the scope of the claims.

Claims

1. A closed-loop control method for electric field stimulation based on electrical impedance imaging, characterized in that, The method is applied in a control terminal, which is communicatively connected to an excitation acquisition unit and an electrical stimulation unit to transmit data information. The excitation acquisition unit and the electrical stimulation unit are respectively electrically connected to an electrode array, which is worn at the stimulation site. The method includes: The voltage change information obtained by the excitation acquisition unit is acquired based on the input initial control parameters. The voltage change information and user breathing data are coupled based on the input detection image to obtain the corresponding digital twin model; The sensitive fields corresponding to each excitation measurement combination are obtained based on the digital twin model and the excitation constant current in the initial control parameters. Differential imaging is performed on the sensitive field based on the user's breathing data and the digital twin model to obtain the corresponding reconstructed image; The reconstructed image is assigned an absolute conductivity value based on the digital twin model to obtain the corresponding absolute conductivity assignment result; The initial control parameters are convexly optimized according to the preset convex optimization rules and the absolute conductivity assignment results to obtain the corresponding target optimization parameters; Based on the target optimization parameters, corresponding control commands are generated and sent to the electrical stimulation unit to control the electrode array. The step of performing differential imaging on the sensitive field based on the user's breathing data and the digital twin model to obtain the corresponding reconstructed image includes: The complete breathing phase is divided based on the user's breathing data to obtain multiple corresponding breathing phases; The breathing phases are coupled according to the digital twin model to generate conductivity images corresponding to each breathing phase; Based on the sensitive field and the objective function, the conductivity image is reconstructed to obtain the image corresponding to the minimum function value of the objective function as the reconstructed image. The step of reconstructing the conductivity image based on the sensitive field and the target function, and obtaining the image corresponding to the minimum function value of the target function as the reconstructed image, includes: Based on the digital twin model, the measured phase position corresponding to the average voltage measurement in the voltage change information is obtained; Based on the respiratory phase, obtain the conductivity label of the phase adjacent to the measured phase in the conductivity image; Based on the cross-gradient coupling algorithm and the conductivity distribution corresponding to the conductivity image, cross-gradient calculations are performed on the conductivity labels of adjacent phases to obtain the gradient values ​​corresponding to each conductivity label. The conductivity distribution corresponding to the conductivity image, the voltage measurement value in the voltage change information, and the gradient value are input into the target function to calculate the corresponding function value; The conductivity image is reconstructed based on the change in the function value of the objective function, so as to obtain the image when the function value of the objective function is minimized as the reconstructed image.

2. The closed-loop control method for electric field stimulation based on electrical impedance imaging according to claim 1, characterized in that, The step of obtaining the sensitive field corresponding to each excitation measurement combination based on the digital twin model and the excitation constant current in the initial control parameters includes: The digital twin model is meshed, and the corresponding stiffness matrix is ​​constructed based on the mesh elements obtained from the meshing. The corresponding potential distribution is calculated based on the constant excitation current and the stiffness matrix; Obtain the sensitive field corresponding to each excitation measurement combination and the potential distribution.

3. The closed-loop control method for electric field stimulation based on electrical impedance imaging according to claim 1 or 2, characterized in that, The step of assigning an absolute conductivity value to the reconstructed image based on the digital twin model to obtain the corresponding absolute conductivity assignment result includes: The reconstructed image is normalized to obtain the corresponding normalized image; The normalized image is assigned an absolute conductivity value based on the digital twin model to obtain the corresponding absolute conductivity assignment result.

4. The closed-loop control method for electric field stimulation based on electrical impedance imaging according to claim 3, characterized in that, The step of performing convex optimization on the initial control parameters according to the preset convex optimization rules and the absolute conductivity assignment result to obtain the corresponding target optimization parameters includes: The corresponding lead field matrix is ​​calculated based on the electric field distribution of each given current vector in the absolute conductivity assignment result. The initial control parameters are convexly optimized based on the optimization function in the convex optimization rule and the lead field matrix to obtain the corresponding target optimization parameters.

5. The closed-loop control method for electric field stimulation based on electrical impedance imaging according to claim 3, characterized in that, The step of obtaining the voltage change information measured by the excitation acquisition unit based on the input initial control parameters includes: An initial control command is generated based on the initial control parameters and sent to the excitation acquisition unit. The initial state voltage measurement and calibration measurement signal are obtained from the excitation acquisition unit to obtain calibration measurement information. Based on the initial control parameters, sequential excitation commands for adjacent electrodes are generated and sent to the excitation acquisition unit to obtain voltage change measurement information obtained by the excitation acquisition unit during the complete breathing process. The calibration measurement information and the voltage change measurement information are combined to obtain the corresponding voltage change information.

6. A closed-loop control device for electric field stimulation based on electrical impedance imaging, characterized in that, The device is configured in a control terminal, which is communicatively connected to the excitation acquisition unit and the electrical stimulation unit to transmit data information. The excitation acquisition unit and the electrical stimulation unit are respectively electrically connected to an electrode array, which is worn at the stimulation site. The device is used to execute the closed-loop control method for electric field stimulation based on electrical impedance imaging as described in any one of claims 1-5. The device includes: A voltage change information acquisition unit is used to acquire voltage change information measured by the excitation acquisition unit based on the input initial control parameters. The coupling unit is used to couple the voltage change information and the user's breathing data according to the input detection image to obtain the corresponding digital twin model; The sensitive field acquisition unit is used to acquire the sensitive field corresponding to each excitation measurement combination based on the digital twin model and the excitation constant current in the initial control parameters. The image reconstruction acquisition unit is used to perform differential imaging on the sensitive field based on the user's breathing data and the digital twin model to obtain the corresponding reconstructed image; The assignment unit is used to assign an absolute conductivity value to the reconstructed image according to the digital twin model, and obtain the corresponding absolute conductivity assignment result; An optimization unit is used to perform convex optimization on the initial control parameters according to a preset convex optimization rule and the absolute conductivity assignment result, so as to obtain the corresponding target optimization parameters. A control command sending unit is used to generate corresponding control commands based on the target optimization parameters and send them to the electrical stimulation unit so as to control the electrode array through the electrical stimulation unit.

7. A computer device, characterized in that, The device includes a processor, a communication interface, a memory, and a communication bus, wherein the processor, the communication interface, and the memory communicate with each other through the communication bus; Memory, used to store computer programs; When a processor executes a program stored in a memory, it implements the steps of the closed-loop control method for electric field stimulation based on electrical impedance imaging as described in any one of claims 1-5.

8. A computer-readable storage medium having a computer program stored thereon, characterized in that, When the computer program is executed by the processor, it implements the steps of the closed-loop control method for electric field stimulation based on electrical impedance imaging as described in any one of claims 1-5.

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