A magnetic drainage regulation device and method based on subcortical functional atlas

Abstract

The application discloses a subcortical functional atlas-based magnetic drainage regulation device and method, comprising: an acquisition module for acquiring an individualized brain atlas model based on a subcortical functional atlas; a regulation module for determining the position of a subcortical deep nucleus stimulation target according to the individualized brain atlas model and assisting transcranial direct current stimulation with a drainage magnetic field to perform deep nucleus stimulation regulation; wherein the position of the stimulation target is taken as an electromagnetic focusing center, and the drainage magnetic field is formed through a magnetic source coil; and a feedback module for dynamically adjusting the magnetic source coil according to a stimulation result to realize safe and accurate regulation of the target. The technical scheme of the application can solve the problem that transcranial direct current stimulation is difficult to balance stimulation safety and stimulation depth.

Description

Technical Field

[0001] This invention belongs to the field of neural network regulation technology, and particularly relates to a magnetic flow regulation device and method based on subcortical functional maps. Background Technology

[0002] With the deepening of population aging, increasing life competition pressure, and changes in the external environment, the number of patients with neurodegenerative diseases, drug-resistant epilepsy, mental illnesses, and other functional brain disorders has surged, becoming one of the leading causes of disability and death worldwide. This not only places a heavy burden on individuals and society, but the research into their treatment methods and mechanisms remains a pressing scientific challenge. Against this backdrop of the severe global burden of functional brain disorders, neuromodulation has become one of the fastest-growing areas in medicine, thanks to advancements in neuroscience and biomedical engineering. As a biomedical engineering technology that utilizes implantable or non-implantable techniques, employing physical (electric, magnetic, optical, ultrasonic, etc.) or chemical methods to excite, inhibit, or regulate the nervous system, thereby improving patients' quality of life and enhancing their neurological function, tens of thousands of patients with functional brain disorders worldwide have already benefited from it.

[0003] Transcranial direct current stimulation (tDCS), as one of the most mature non-invasive neuromodulation techniques, exerts its regulatory effect by modulating the activity of neural networks through a constant, low-intensity direct current (1-2 mA). At the neuronal level, the basic mechanism of tDCS in regulating cortical excitability is based on changes in the resting membrane potential caused by different polarities of stimulation. Anodic stimulation usually increases cortical excitability, while cathodic stimulation decreases it. Placing the anode directly above the target point on the scalp is a common stimulation method. However, this traditional approach has two drawbacks. First, the diffuse conduction of current within the brain makes it difficult to ensure targeted stimulation of the target area. Second, to stimulate deep cortical areas, given a certain impedance, the only way to achieve stimulation is to increase the current magnitude. However, to avoid patient discomfort, electrical stimulation has strict limitations on current magnitude and density. Therefore, it is difficult to achieve a balance between stimulation safety and stimulation depth in transcranial direct current stimulation. Summary of the Invention

[0004] The technical problem to be solved by the present invention is to provide a magnetic drainage control device and method based on subcortical functional maps, so as to solve the problem that it is difficult to achieve a balance between stimulation safety and stimulation depth in transcranial direct current stimulation.

[0005] To achieve the above objectives, the present invention adopts the following technical solution:

[0006] A magnetic drainage modulation device based on subcortical functional mapping includes:

[0007] The acquisition module is used to acquire individualized brain atlas models based on subcortical functional atlases;

[0008] The control module is used to determine the location of the stimulation target point of the deep subcortical nuclei according to the individualized brain atlas model and to perform deep nucleus stimulation control by transcranial direct current stimulation assisted by the drainage magnetic field; wherein, the location of the stimulation target point is used as the electromagnetic focusing center, and the drainage magnetic field is formed by the magnetic source coil.

[0009] The feedback module is used to dynamically adjust the magnetic source coil based on the stimulus result to achieve safe and precise control of the target point.

[0010] Preferably, the acquisition module includes:

[0011] The first building unit is used to perform three-dimensional structural reconstruction based on the structural MRI image data of the controlled object, and divide it into a multi-layered tissue model of scalp, skull, cerebrospinal fluid, gray matter and white matter to obtain a three-dimensional cranial brain model.

[0012] The second building block is used to obtain an individualized subcortical functional map based on the functional MRI data of the controlled object.

[0013] The third building unit is used to correct and match the three-dimensional cranial model with the individualized subcortical functional atlas to obtain an individualized brain atlas model.

[0014] Preferably, the control module includes:

[0015] The target determination unit is used to obtain the relative spatial coordinates of the selected target in the personalized brain mapping model and accurately locate it in the personalized brain mapping model.

[0016] The stimulation control unit is used to set the area where the drainage magnetic field intersects with the scalp as the electrode placement area for transcranial direct current stimulation; and to realize the drainage control of deep brain target points by microcurrent transcranial direct current stimulation according to the placement method of the anode and cathode of the electrodes in the transcranial direct current stimulation electrode placement area and the current direction in the magnetic source coil.

[0017] Preferably, the feedback module includes:

[0018] The result evaluation unit is used to evaluate the stimulation focus and stimulation safety of the stimulation target point of the deep subcortical nucleus and within a 1 cm radius of the stimulation target point.

[0019] The dynamic optimization unit is used to dynamically adjust and optimize the magnetic source coil based on the evaluation results of stimulation focus and stimulation safety. It adjusts the posture and position of the field source coil and the magnitude of the current in the coil to achieve the precise drainage effect of the magnetic field on the target point of the transcranial current.

[0020] This invention also provides a magnetic drainage modulation method based on subcortical functional maps, comprising the following steps:

[0021] Step S1: Obtain an individualized brain atlas model based on subcortical functional atlas;

[0022] Step S2: Based on the individualized brain atlas model, determine the location of the stimulation target point of the deep subcortical nuclei and perform deep nucleus stimulation modulation by transcranial direct current stimulation assisted by a drainage magnetic field; wherein, the location of the stimulation target point is used as the electromagnetic focusing center, and the drainage magnetic field is formed by a magnetic source coil;

[0023] Step S3: Dynamically adjust the magnetic source coil according to the stimulation result to achieve safe and precise control of the target point.

[0024] Preferably, step S1 includes:

[0025] Based on the structural MRI data of the controlled object, a three-dimensional structural reconstruction was performed, and the object was divided into a multi-layered tissue model consisting of scalp, skull, cerebrospinal fluid, gray matter, and white matter, thus obtaining a three-dimensional cranial brain model.

[0026] Based on the functional MRI data of the subjects, individualized subcortical functional maps were obtained;

[0027] The three-dimensional cranial model is corrected and matched with the individualized subcortical functional atlas to obtain an individualized brain atlas model.

[0028] Preferably, step S2 includes:

[0029] In the personalized brain mapping model, the relative spatial coordinates of the selected target point are obtained and accurately located in the personalized brain mapping model;

[0030] The area where the drainage magnetic field intersects with the scalp is designated as the electrode placement area for transcranial direct current stimulation; and based on the placement method of the anode and cathode of the electrodes in the transcranial direct current stimulation electrode placement area and the current direction in the magnetic source coil, the drainage regulation of deep target points of the brain by microcurrent transcranial direct current stimulation is realized.

[0031] Preferably, step S3 includes:

[0032] The stimulation focus and safety of the deep subcortical nuclei stimulation target points and the area within a 1 cm radius centered on the stimulation target points were evaluated.

[0033] Based on the evaluation results of stimulation focus and stimulation safety, the magnetic source coil is dynamically adjusted and optimized, including the adjustment of the posture and position of the field source coil and the magnitude of the current in the coil, so as to achieve the precise drainage effect of the magnetic field on the target point of transcranial current.

[0034] This invention constructs a stable magnetic field that directionally constrains the current beam to the target point, thereby enabling focused stimulation modulation of the deep brain by transcranial direct current stimulation, which can improve the focus and stimulation depth of transcranial direct current stimulation. Attached Figure Description

[0035] Figure 1 This is a schematic diagram of the magnetic drainage control device based on subcortical functional maps according to an embodiment of the present invention;

[0036] Figure 2 This is a schematic diagram illustrating the principle of magnetically confined transcranial direct current stimulation drainage in an embodiment of the present invention.

[0037] Figure 3 This is a flowchart of a magnetic drainage regulation method based on subcortical functional maps, according to an embodiment of the present invention. Detailed Implementation

[0038] 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 embodiments of the present invention, and not all embodiments. 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.

[0039] To make the above-mentioned objects, features and advantages of the present invention more apparent and understandable, the present invention will be further described in detail below with reference to the accompanying drawings and specific embodiments.

[0040] Example 1:

[0041] like Figure 1 , 2 As shown, the present invention provides a magnetic drainage modulation device based on subcortical functional maps, comprising:

[0042] The acquisition module is used to acquire individualized brain atlas models based on subcortical functional atlases;

[0043] The control module is used to determine the location of the stimulation target point of the deep subcortical nuclei based on the individualized brain mapping model, and to perform deep nucleus stimulation control through transcranial direct current stimulation assisted by a drainage magnetic field. Specifically, the drainage magnetic field is formed by a magnetic source coil using the location of the stimulation target point as the electromagnetic focusing center. Using the deep subcortical nucleus stimulation target point as the electromagnetic focusing center, a spindle-shaped magnetic field is designed based on the magnetic mirror effect, so that the electron flow can be confined in a fixed pathway, and the maximum intracranial current density is reached at the deep subcortical nucleus stimulation target point. According to the required magnetic field, a drainage magnetic field is formed by arranging multiple magnetic source coils outside the brain, i.e., a stable magnetic field is formed after energization, creating a relative magnetic potential trap at the stimulation target point location within the brain.

[0044] The feedback module is used to dynamically adjust the magnetic source coil based on the stimulus result to achieve precise and safe control of the target point.

[0045] As one embodiment of the present invention, the acquisition module includes:

[0046] The first building unit is used to perform three-dimensional structural reconstruction based on the structural MRI image data of the controlled object, and divide it into a multi-layered tissue model of scalp, skull, cerebrospinal fluid, gray matter and white matter to obtain a three-dimensional cranial brain model.

[0047] The second building block is used to obtain an individualized subcortical functional map based on the functional MRI data of the controlled object.

[0048] The third building unit is used to correct and match the three-dimensional cranial model with the individualized subcortical functional atlas to obtain an individualized brain atlas model.

[0049] As one embodiment of the present invention, the control module includes:

[0050] The target determination unit is used to obtain the relative spatial coordinates of the selected target in the personalized brain mapping model and accurately locate it in the personalized brain mapping model.

[0051] The stimulation control unit is used to designate the area where the drainage magnetic field intersects with the scalp as the electrode placement area for transcranial direct current stimulation (DCPS). Based on the placement of the anode and cathode of the electrodes in the DCPS electrode placement area and the current direction within the magnetic source coil, it achieves microcurrent DCPS stimulation to regulate the drainage of deep brain targets. Specifically, designating the area where the drainage magnetic field intersects with the scalp as the DCPS electrode placement area involves: finding the intersection area between the magnetic field lines formed by the magnetic source coil and the scalp, defining it as the starting point for electron flow constraint, and thus setting it as the DCPS electrode placement area.

[0052] As one embodiment of the present invention, the feedback module includes:

[0053] The result evaluation unit is used to evaluate the stimulation focus and stimulation safety of the stimulation target point of the deep subcortical nucleus and the area within a 1cm radius centered on the stimulation target point. The stimulation target point of the deep subcortical nucleus and the area within a 1cm radius centered on the stimulation target point are referred to as the target area.

[0054] The dynamic optimization unit is used to dynamically adjust and optimize the magnetic source coil based on the evaluation results of stimulation focus and stimulation safety.

[0055] Furthermore, in the result evaluation unit, regarding stimulus focusing, the change in the amount of charge flowing through the target area is calculated, and its electric field distribution is monitored, thereby obtaining the improvement effect of stimulus focusing under a steady magnetic field; wherein,

[0056] The formula for calculating the change in the amount of charge flowing through is:

[0057] ΔQ=(I after -I before )×T

[0058] Where ΔQ represents the change in charge flowing through the target region before and after magnetic attraction, and I after with I before To monitor the current value in the target area during the simulation, T is the time of one transcranial direct current stimulation cycle.

[0059] Furthermore, in the result evaluation unit, regarding stimulation safety, the heat generated by the current loop flowing through various intracranial tissues is calculated, the maximum current within its region is monitored, and it is determined whether it exceeds the maximum tolerance value; wherein,

[0060] The formula for calculating the heat generated by the current loop flowing through various intracranial tissues is as follows:

[0061]

[0062] Where J represents the heat generated intracranially by the current loop, and I... 2 (l) represents the current value per unit length due to the difference in conductivity at different tissue locations caused by the current loop, which is a function of location. σ is the conductivity of the tissue at that location, S is the cross-sectional area of ​​the current conduction path, and T is the time of one transcranial direct current stimulation cycle.

[0063] Furthermore, the dynamic optimization unit dynamically adjusts and optimizes the magnetic source coil based on the stimulation focus and safety assessment results to optimize the stimulation effect. Specifically, by comparing the charge increment flowing through the target area, and considering the stimulation gain effect of the magnetic confinement on the direction of electron flow, if the target area is not the maximum gain region, the orientation and position of the magnetic source coil are shifted towards the direction of the maximum gain region; if the magnetic field confinement is insufficient, the magnetic source current is increased, ultimately causing the magnetic field confinement area to shift towards the target area, that is, simultaneously moving the maximum gain region towards the target area until it is covered by it.

[0064] Example 2:

[0065] like Figure 3 As shown, the present invention also provides a magnetic drainage modulation method based on subcortical functional maps, comprising the following steps:

[0066] Step S1: Obtain an individualized brain atlas model based on subcortical functional atlas;

[0067] Step S2: Based on the individualized brain atlas model, determine the location of the stimulation target point of the deep subcortical nuclei and perform deep nucleus stimulation modulation by transcranial direct current stimulation assisted by a drainage magnetic field; wherein, the location of the stimulation target point is used as the electromagnetic focusing center, and the drainage magnetic field is formed by a magnetic source coil;

[0068] Step S3: Dynamically adjust the magnetic source coil according to the stimulation result to achieve safe and precise control of the target point.

[0069] As one embodiment of the present invention, step S1 includes:

[0070] Based on the structural MRI data of the controlled object, a three-dimensional structural reconstruction was performed, and the object was divided into a multi-layered tissue model consisting of scalp, skull, cerebrospinal fluid, gray matter, and white matter, thus obtaining a three-dimensional cranial brain model.

[0071] Based on the functional MRI data of the subjects, individualized subcortical functional maps were obtained;

[0072] The three-dimensional cranial model is corrected and matched with the individualized subcortical functional atlas to obtain an individualized brain atlas model.

[0073] As one embodiment of the present invention, step S2 includes:

[0074] In the personalized brain mapping model, the relative spatial coordinates of the selected target point are obtained and accurately located in the personalized brain mapping model;

[0075] The area where the drainage magnetic field intersects with the scalp is designated as the electrode placement area for transcranial direct current stimulation; and based on the placement method of the anode and cathode of the electrodes in the transcranial direct current stimulation electrode placement area and the current direction in the magnetic source coil, the drainage regulation of deep target points of the brain by microcurrent transcranial direct current stimulation is realized.

[0076] As one embodiment of the present invention, step S3 includes:

[0077] The stimulation focus and safety of the deep subcortical nuclei stimulation target points and the area within a 1 cm radius centered on the stimulation target points were evaluated.

[0078] Based on the evaluation results of stimulation focus and stimulation safety, the magnetic source coil is dynamically adjusted and optimized.

[0079] 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 variations or substitutions that can be easily conceived by those skilled in the art within the technical scope of the present invention should be included 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 magnetic drainage control device based on subcortical functional mapping, characterized in that, include: The acquisition module is used to acquire individualized brain atlas models based on subcortical functional atlases; The control module is used to determine the location of the stimulation target point of the deep subcortical nuclei according to the individualized brain atlas model and to perform deep nucleus stimulation control by transcranial direct current stimulation assisted by the drainage magnetic field; wherein, the location of the stimulation target point is used as the electromagnetic focusing center, and the drainage magnetic field is formed by the magnetic source coil. The feedback module is used to dynamically adjust the magnetic source coil according to the stimulus result to achieve safe and precise control of the target point; The acquisition module includes: The first building unit is used to perform three-dimensional structural reconstruction based on the structural MRI image data of the controlled object, and divide it into a multi-layered tissue model of scalp, skull, cerebrospinal fluid, gray matter and white matter to obtain a three-dimensional cranial brain model. The second building block is used to obtain an individualized subcortical functional map based on the functional MRI data of the controlled object. The third building unit is used to correct and match the three-dimensional cranial model with the individualized subcortical functional atlas to obtain an individualized brain atlas model.

2. The magnetic drainage control device based on subcortical functional mapping as described in claim 1, characterized in that, The control module includes: The target determination unit is used to obtain the relative spatial coordinates of the selected target in the personalized brain mapping model and accurately locate it in the personalized brain mapping model. The stimulation control unit is used to set the area where the drainage magnetic field intersects with the scalp as the electrode placement area for transcranial direct current stimulation; and to realize the drainage control of deep brain target points by microcurrent transcranial direct current stimulation according to the placement method of the anode and cathode of the electrodes in the transcranial direct current stimulation electrode placement area and the current direction in the magnetic source coil.

3. The magnetic drainage control device based on subcortical functional mapping as described in claim 2, characterized in that, The feedback module includes: The result evaluation unit is used to evaluate the stimulation focus and stimulation safety of the stimulation target point of the deep subcortical nucleus and within a 1 cm radius of the stimulation target point. The dynamic optimization unit is used to dynamically adjust and optimize the magnetic source coil based on the evaluation results of stimulation focus and stimulation safety. It adjusts the posture and position of the field source coil and the magnitude of the current in the coil to achieve the precise drainage effect of the magnetic field on the target point of the transcranial current.

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