A simulation device for precise positioning of a brain-computer interface stimulation target

Abstract

The utility model discloses a kind of simulation devices for brain-computer interface stimulation target point accurate positioning, belong to the time interference electric stimulation technical field of brain-computer interface regulation and control technology regulation and control side. The device includes skull model, the skull model has transparent head mould, the transparent head mould is equipped with electrode sheet, and inside is filled with brain tissue equivalent liquid, the output end of the electrode sheet is equipped with cerebral cortex dummy conduction piece, the input end of the electrode sheet is equipped with equipment host, the skull model is equipped with probe and target point feedback ware in the transparent head mould, the probe is electrically connected with the target point feedback ware and the equipment host respectively. The utility model is suitable for simulating verification to TI stimulation scheme before patient treatment, can achieve to copy patient head simulation model, realize the visualization presentation of target point feedback ware to interference focal point, and provide experimental verification, and can be real-time dynamic correction, satisfy the purpose of clinical precise treatment demand.

Description

Technical Field

[0001] This invention belongs to the field of time-interference electrical stimulation technology of brain-computer interface modulation technology, and particularly relates to a simulation device for precise positioning of brain-computer interface stimulation target points. Background Technology

[0002] Brain-computer interface modulation refers to the real-time acquisition and decoding of brain neural signals through a brain-computer interface (BCI), and the automatic or closed-loop control of external neural stimulation devices (TMS / TI / tFUS / electric stimulation, etc.) based on the decoding results to achieve precise, adaptive, and closed-loop intervention of brain activity, behavior, or pathological states.

[0003] Among them, the time-interference electrical stimulation in the control end is a non-invasive, precise, and deep-targeting transcranial electrical stimulation technology. The core is to use two high-frequency currents to interfere and generate a low-frequency envelope in the brain, so as to achieve precise control of deep nuclei (such as the hippocampus and striatum).

[0004] Existing time-interference electrostimulation (TI) target localization methods typically construct a three-dimensional head model based on the patient's T1-weighted magnetic resonance imaging (MRI) images and use finite element simulation software to calculate the electric field and theoretically predict the location of the interference focus in deep brain regions. However, this method has significant drawbacks: First, the simulation relies on the average values ​​of general tissue electromagnetic parameters, failing to reflect individual patient impedance differences. Second, structures such as the skull and brain tissue are simplified as homogeneous media, deviating from actual anatomical structures. Third, it is only a computer-generated virtual calculation, lacking real physical electric field monitoring and feedback, making it impossible to verify the focus position, intensity, and focusing accuracy through actual measurement. Fourth, it cannot correct target deviation in real time during stimulation, easily leading to inaccurate stimulation location, decreased treatment efficacy, and activation of non-target areas. Fifth, it is difficult to accurately model actual influencing factors such as electrode contact impedance and cerebrospinal fluid distribution.

[0005] It is evident that existing TI target localization methods based on T1 and finite element simulation only remain at the theoretical prediction level, and have fundamental defects such as insufficient individualization, limited accuracy, lack of experimental verification, and inability to perform real-time correction, making it difficult to meet the needs of precise clinical treatment. Utility Model Content

[0006] The purpose of this invention is to address the problems existing in the prior art by providing a simulation device for precise localization of stimulation targets in brain-computer interfaces.

[0007] To achieve the above objectives, the utility model adopts the following technical solution: a simulation device for precise localization of stimulation targets in a brain-computer interface, comprising a head model, the head model having a transparent head mold, the transparent head mold having electrode pads and being filled with brain tissue equivalent fluid, the output end of the electrode pads having a cerebral cortex phantom conductor, the input end of the electrode pads having a device host, the head model having a detector and a target feedback device located within the transparent head mold, the detector being electrically connected to the target feedback device and the device host respectively, to form a target visual feedback link for indicating stimulation target parameters.

[0008] By employing the above technical solution, brain tissue equivalent fluid is injected into the transparent head mold of the skull model to replicate the impedance characteristics of the patient's brain tissue. Then, two pairs of positive and negative electrode pads are installed on the transparent head mold and electrically connected to the main unit of the device. When the main unit of the device is working, the target point on the target feedback device will change color. At this time, the doctor can observe from the outside whether the target point position on the target feedback device is accurate and whether the intensity is within the appropriate range, realizing the visualization of the interference focus of the target feedback device and providing experimental verification.

[0009] As a further technical solution, the electrode sheets are provided at least four, and are arranged in pairs.

[0010] By adopting the above technical solution, since time interference requires two independent current channels to be superimposed in space, one current channel requires two positive and two negative electrodes, and two channels require four electrodes. If there are fewer than four electrodes, a two-dimensional cross interference field cannot be formed in space. Therefore, the number of electrode plates is set to at least four, and they must be used in pairs.

[0011] As a further technical solution, the cerebral cortex phantom conductive element is located inside the transparent head mold; the cerebral cortex phantom conductive element receives the output signal of the electrode sheet and transmits it to the brain tissue equivalent fluid so that the detector receives its conducted signal.

[0012] By adopting the above technical solution, if the electrode sheet and the brain tissue equivalent fluid are in direct contact, the signal may be attenuated or distorted due to unstable interface impedance. The cerebral cortex phantom conductive component uses a low-polarization, high-stability conductive material to form a stable solid-liquid electrical contact interface, ensuring that the signal is efficiently injected into the brain tissue equivalent fluid.

[0013] As a further technical solution, the main unit of the device is electrically connected to the electrode plate via electrode wires.

[0014] By adopting the above technical solution, the high-frequency electrical signal generated inside the device host is transmitted to the electrode plate through the electrode wire in a low-loss and low-interference manner, so that the signal can be transmitted stably.

[0015] As a further technical solution, the detector and target feedback device are mounted on the head model, so that the brain tissue is encapsulated in equivalent fluid, and the feedback signal of the target feedback device can be observed externally through the transparent head model.

[0016] By adopting the above technical solution, based on the linkage between the detector's detection and the target feedback device's light transmission feedback, a physical perception basis and a visual decision-making basis are provided for the subsequent dynamic correction of the equipment host parameters.

[0017] As a further technical solution, the head model is a 3D printed head mold, and the internal cavity shape of the transparent head mold matches the anatomical structure of the patient's head.

[0018] By adopting the above technical solution, the thickness, density, irregular contours of the patient's skull and the spatial distribution of intracranial brain regions can be replicated, avoiding simulation errors in target localization.

[0019] As a further technical solution, the brain tissue equivalent fluid is a conductive liquid, and its impedance characteristics match the impedance characteristics of the patient's brain tissue.

[0020] By adopting the above technical solution, the average value of tissue electromagnetic parameters commonly used in existing simulations can be replaced, thus avoiding the problem of target point calculation deviation caused by individual impedance differences.

[0021] As a further technical solution, the target visual feedback link includes a differential-to-single-ended converter, a peak detector, a non-inverting gain amplifier, a high-pass filter, and a low-pass filter connected in sequence, which convert the detector-acquired signal into the target feedback drive signal of the target feedback device.

[0022] By adopting the above technical solution, the electric field signal is processed and converted into a driving signal for the target feedback device, which causes changes in the brightness, flashing frequency and position of the target point on the target feedback device and presents them visually. This allows adjustment of the high-frequency signal parameters of the time device host to perform target positioning and intensity adaptation.

[0023] Compared with the prior art, the beneficial effects of this utility model are: 1. This application replicates a patient's head simulation model through the structural design of a head model, electrode pads, a cerebral cortex phantom conductive device, a detector, and a target feedback device. This allows the detector to collect the electric field intensity, interference envelope distribution, and focal position of different regions in the brain tissue equivalent fluid filled inside the transparent head model during TI stimulation. This enables the target feedback device to visualize the interference focal point, providing experimental verification and meeting the needs of precise clinical treatment. 2. This application uses the device host to apply a high-frequency signal to the brain tissue equivalent fluid through electrode pads and cerebral cortex phantom conductive components, so that the signal collected by the detector is converted into the target feedback drive signal of the target feedback device. When the detector detects that the interference focus is deviated from the target brain region, it can adjust the high-frequency signal parameters output by the device host in reverse, which can be dynamically corrected in real time. Attached Figure Description

[0024] Figure 1 This is a schematic diagram of the overall structure of the simulation device for precise localization of stimulation targets in brain-computer interfaces according to this utility model. Figure 2 This is a schematic diagram of the electrode pads arranged on a skull model in the simulation device for precise localization of stimulation targets in a brain-computer interface according to this utility model. Figure 3 This is a schematic diagram of the target feedback state of the simulation device for precise positioning of brain-computer interface stimulation targets according to this utility model. Figure 3 (a) is a schematic diagram of the feedback state of target point 1 in the simulation device for precise positioning of brain-computer interface stimulation target points of this utility model; Figure 3 (b) is a schematic diagram of the feedback state of target point 2 in the simulation device for precise positioning of brain-computer interface stimulation target points of this utility model; Figure 3 (c) is a schematic diagram of the feedback state of target point 3 in the simulation device for precise positioning of brain-computer interface stimulation target points of this utility model. Figure 4 This invention relates to a target visual feedback link for a brain-computer interface stimulation target precise positioning simulation device.

[0025] In the diagram: 1. Transparent head mold; 2. Electrode pads; 3. Cerebral cortex phantom conductive element; 4. Electrode wires; 5. Main unit of the device; 6. Detector; 7. Target feedback device. Detailed Implementation

[0026] The technical solution of this utility model will now be clearly and completely described with reference to the accompanying drawings. Obviously, the described embodiments are only a part of the embodiments of this utility model, and not all of them. Based on the embodiments of this utility model, all other embodiments obtained by those skilled in the art without creative effort are within the scope of protection of this utility model.

[0027] In the description of this utility model, it should be noted that the terms "middle", "upper", "lower", "left", "right", "inner", "outer", etc., indicate the orientation or positional relationship based on the orientation or positional relationship shown in the accompanying drawings. They are only for the convenience of describing this utility model and simplifying the description, and do not indicate or imply that the device or element referred to must have a specific orientation, or be constructed and operated in a specific orientation. Therefore, they should not be construed as limitations on this utility model.

[0028] like Figure 1-4 As shown, the specific scheme of the embodiment is as follows: A simulation device for precise localization of stimulation targets in a brain-computer interface includes a head model, the head model having a transparent head mold 1, an electrode plate 2 on the transparent head mold 1, and the interior being filled with brain tissue equivalent fluid, the output end of the electrode plate 2 having a cerebral cortex phantom conductor 3, the input end of the electrode plate 2 having a device host 5, the head model having a detector 6 and a target feedback device 7 located inside the transparent head mold 1, the detector 6 being electrically connected to the target feedback device 7 and the device host 5 respectively, to form a target visual feedback link for indicating stimulation target parameters.

[0029] In use, two pairs of positive and negative electrode pads 2 are selected, and brain tissue equivalent fluid is injected into the transparent head mold 1 of the skull model to replicate the impedance characteristics of the patient's brain tissue. Then, two pairs of positive and negative electrode pads 2 are installed on the transparent head mold 1 (e.g., Figure 2 As shown, the first pair of electrode plates are A+ and A-; the second pair of electrode plates are B+ and B-), and are electrically connected to the main unit 5. Simultaneously, a detector 6 and a target feedback device 7 are installed inside the transparent head mold 1. When the main unit 5 is working, the target point on the target feedback device 7 will change color, such as... Figure 3 As shown, the brightness of the color indicates the intensity of the stimulus. At this time, the doctor can observe from the outside whether the target position on the target feedback device 7 is accurate and whether the intensity is within the appropriate range, so as to realize the visualization of the interference focus of the target feedback device 7 and provide experimental verification. Then, by adjusting the two high-frequency current parameters output by the host device 5, the target position and intensity of the target feedback device 7 can be matched, and real-time dynamic correction can be achieved to meet the needs of precise clinical treatment.

[0030] In this embodiment, the head model is a 3D printed head mold, and the inner cavity shape of the transparent head mold 1 matches the anatomical structure of the patient's head.

[0031] Specifically, T1-weighted magnetic resonance images of the patient's head are obtained, and a 1:1 individualized 3D model that is completely consistent with the patient's skull anatomy is constructed through 3D reconstruction technology. A physical skull model is prepared using 3D printing technology to replicate the thickness, density, irregular contours of the patient's skull and the spatial distribution of intracranial brain regions, thus avoiding simulation errors in target localization.

[0032] It should be noted that the skull model is divided into a transparent head mold 1 and a facial model part that simulates the facial contours. The transparent head mold 1 has a sealing ring at the edge of the opening and is snapped into the facial model part, and then fixed with screws to prevent leakage of brain tissue equivalent fluid. In addition, a through hole is provided on the face model part, and an adapter plug is provided in the through hole for sealing. The through hole allows brain tissue equivalent fluid to be injected or discharged into the transparent head model 1.

[0033] To further explain, the dominant factors in the electric field distribution of TI electrical stimulation are the high electrical impedance barrier of the skull and the conductivity of brain tissue. The subcutaneous soft tissue is thinner and its impedance is relatively small compared to that of brain tissue. Therefore, its influence on the electric field distribution can be ignored in engineering or considered together with the brain tissue equivalent fluid.

[0034] In this embodiment, the brain tissue equivalent fluid is a conductive liquid whose impedance characteristics match those of the patient's brain tissue.

[0035] It should be noted that in bioelectric simulation, commonly used brain tissue equivalent solutions include physiological saline, agar gel, and polyacrylamide gel, and the impedance characteristics of the tissue can be matched by adjusting the concentration of conductive ions.

[0036] Specifically, brain tissue equivalent fluid is injected into the 3D-printed transparent head model 1. The conductivity and dielectric constant of the brain tissue equivalent fluid are completely matched with the impedance characteristics of the patient's real brain tissue (including gray matter, white matter, and cerebrospinal fluid), replacing the average value of tissue electromagnetic parameters commonly used in existing simulations, thus avoiding the target calculation deviation problem caused by individual impedance differences.

[0037] In this embodiment, at least four electrode sheets 2 are provided, and they are arranged in pairs.

[0038] It should be noted that since time interference requires two independent current channels to be superimposed in space, one current channel requires two electrodes (positive and negative), and two current channels require four electrodes. Fewer than four electrodes cannot form a two-dimensional cross interference field in space. Therefore, the number of electrode plates 2 is set to at least four, and they must be used in pairs.

[0039] In this embodiment, the cerebral cortex phantom conductive element 3 is located inside the transparent head mold 1; the cerebral cortex phantom conductive element 3 receives the output signal of the electrode sheet 2 and transmits it to the brain tissue equivalent fluid so that the detector 6 receives its conducted signal.

[0040] It should be noted that if the electrode 2 (metal / conductive gel material) comes into direct contact with the brain tissue equivalent fluid, the signal may be attenuated or distorted due to unstable interface impedance. The cerebral cortex phantom conductive element 3 uses a low-polarization, high-stability conductive material to form a stable solid-liquid electrical contact interface, ensuring that the signal is efficiently injected into the brain tissue equivalent fluid.

[0041] In this embodiment, the device host 5 is electrically connected to the electrode plate 2 via the electrode wire 4.

[0042] It is understandable that the high-frequency electrical signal generated inside the host device 5 is transmitted to the electrode plate 2 through the electrode line 4 in a low-loss and low-interference manner, so that the signal can be transmitted stably.

[0043] In this embodiment, the detector 6 and the target feedback device 7 are mounted on the head model, which is then encased in brain tissue equivalent fluid. The feedback signal of the target feedback device 7 can be observed externally through the transparent head model 1. The target visual feedback link includes a differential to single-ended converter, a peak detector, a non-inverting gain amplifier, a high-pass filter, and a low-pass filter connected in sequence, which convert the signal collected by the detector 6 into the target feedback drive signal of the target feedback device 7.

[0044] Specifically, such as Figure 1 , Figure 3 as well as Figure 4 As shown, the device host 5 is connected to the electrode plate 2 of the transparent head mold 1 via electrode wire 4. Two pairs of high-frequency signals are applied to the brain tissue equivalent fluid. The probe 6 at the corresponding position of the target point on the target feedback device 7 detects the superimposed electric field signal of the two pairs of high-frequency signals and transmits it to the detector 6. Through the target point visual feedback link formed by the electrical connection between the detector 6 and the target feedback device 7, the electric field signal is processed by the signal transmission links such as differential to single-ended conversion, peak detection, in-phase gain amplification, and high-pass and low-pass filtering, and converted into the driving signal of the target feedback device. This causes the target point on the target feedback device to show changes in brightness, flicker frequency, and position indication, such as... Figure 3 As shown, the change in brightness of the target point is used to indicate the intensity of the envelope electric field at this location; the change in the frequency of the flashing of the target point is used to indicate the frequency of the envelope electric field at this location; the change in the position of the flashing of the target point is used to indicate the target point position stimulated by the time-interference electrical stimulation device; at this time, the doctor can observe from the outside whether the stimulation target point position is accurate and whether the intensity is within the appropriate range, and then adjust the high-frequency signal parameters of the time device host 5 to perform target point positioning and intensity adaptation.

[0045] Although embodiments of the present invention have been shown and described, it will be understood by those skilled in the art that various changes, modifications, substitutions and alterations can be made to these embodiments without departing from the principles and spirit of the present invention, the scope of which is defined by the appended claims and their equivalents.

Claims

1. A simulation device for precise localization of stimulation targets in brain-computer interfaces, characterized in that, The device includes a skull model with a transparent head mold. Electrodes are mounted on the transparent head mold, which is filled with a brain tissue equivalent fluid. The output end of the electrodes is equipped with a cerebral cortex phantom conductor, and the input end of the electrodes is equipped with a device host. The skull model has a detector and a target feedback device located within the transparent head mold. The detector is electrically connected to both the target feedback device and the device host to form a target visual feedback link for indicating stimulation target parameters. The cerebral cortex phantom conductor is located within the transparent head mold. The cerebral cortex phantom conductor receives the output signal from the electrodes and transmits it to the brain tissue equivalent fluid, allowing the detector to receive its transmitted signal.

2. The simulation device for precise localization of stimulation targets in a brain-computer interface according to claim 1, characterized in that: The electrode plates are provided in at least four pairs.

3. The simulation device for precise localization of stimulation targets in a brain-computer interface according to claim 1, characterized in that: The main unit of the device is electrically connected to the electrode plate via electrode wires.

4. The simulation device for precise localization of stimulation targets in brain-computer interfaces according to claim 1, characterized in that: The detector and target feedback device are mounted on the head model, and the feedback signal of the target feedback device can be observed through the transparent head model.

5. The simulation device for precise localization of stimulation targets in brain-computer interfaces according to claim 1, characterized in that: The head model is a 3D printed head mold, and the internal shape of the transparent head mold matches the anatomical structure of the patient's head.

6. The simulation device for precise localization of stimulation targets in a brain-computer interface according to claim 1, characterized in that: The brain tissue equivalent fluid is a conductive liquid, and its impedance characteristics match those of the patient's brain tissue.

7. The simulation device for precise localization of stimulation targets in brain-computer interfaces according to claim 1, characterized in that: The target visual feedback link includes a differential-to-single-ended converter, a peak detector, a non-inverting gain amplifier, a high-pass filter, and a low-pass filter connected in sequence, which convert the detector-acquired signal into the target feedback drive signal of the target feedback device.

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