CN115887932B - Tangential surrounding type space array and system for deep craniocerebral noninvasive focusing stimulation - Google Patents
Tangential surrounding type space array and system for deep craniocerebral noninvasive focusing stimulation Download PDFInfo
- Publication number
- CN115887932B CN115887932B CN202211400947.2A CN202211400947A CN115887932B CN 115887932 B CN115887932 B CN 115887932B CN 202211400947 A CN202211400947 A CN 202211400947A CN 115887932 B CN115887932 B CN 115887932B
- Authority
- CN
- China
- Prior art keywords
- stimulation
- current
- tangential
- deep
- coils
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Active
Links
Landscapes
- Magnetic Treatment Devices (AREA)
Abstract
The invention discloses a tangential surrounding type space array and a tangential surrounding type space array system for deep non-invasive focusing stimulation of cranium and relates to the technical field of cranium electromagnetic stimulation. The space array comprises a plurality of tangential coils which are used for being transversely arranged around the head of a human body and have the same geometric parameters; when the space array works, a plurality of stimulation currents which are in one-to-one correspondence are input to the tangential coils, the stimulation currents are used for generating a plurality of first induction electric field vectors with the characteristics of similar amplitude and smaller included angle at the deep part of the cranium through the tangential coils, and generating a plurality of second induction electric field vectors with the characteristics of larger amplitude difference and larger included angle at the shallow layer of the scalp, so that the superposition effect of the induction electric field at the deep part of the cranium can be enhanced, the stimulation depth is effectively improved, and the purposes of spatially selective stimulation and stimulation focusing improvement are realized. In addition, the optimal stimulation current parameters in the array can be obtained, and the purpose of global optimization of the space array is achieved.
Description
Technical Field
The invention belongs to the technical field of craniocerebral electromagnetic stimulation, and particularly relates to a tangential surrounding type space array and a tangential surrounding type space array system for deep craniocerebral non-invasive focusing stimulation.
Background
Under the severe background that the incidence rate of the global mental diseases is rising year by year and the cardinality of patients is increasingly huge, the mental diseases become a psychological epidemic situation which cannot be ignored, and the mental diseases form serious threat to national physical and mental health and social economic development. As a leading-edge nerve regulation and control means, the transcranial magnetic stimulation technology is one of the four brain science technologies of the 21 st century, has the characteristics of no wound, no pain and no operation, and is widely applied to clinical diagnosis, treatment and scientific research of various mental diseases such as depression, schizophrenia, alzheimer disease and the like.
The stimulating coil is one of the core components of the transcranial magnetic stimulation system, and the geometric structure of the stimulating coil and the position of the stimulating coil relative to the head of a human body directly influence the spatial distribution form of an intracranial induction electric field, so that the stimulating effect is influenced. Before stimulation is implemented, parameters of a stimulation system are set according to different stimulation purposes, and a stimulation pulse sequence with specific time sequence is generated. During stimulation, a stimulation coil is placed over the target region of the head, and then a time-varying pulsed stimulation current is passed through the stimulation coil so as to cause an alternating induced magnetic field to be generated in the space surrounding the stimulation coil. Because the conductivity and the magnetic permeability of biological tissues are not zero, an alternating induction magnetic field can generate an induction electric field in an intracranial target area, and the induction electric field can be used for adjusting the electrophysiological state of neurons in the target area, thereby playing a role in regulating and controlling nerves. In order to effectively regulate and control target zone nerve tissue and reduce the influence on non-target zone neurons so as to reduce the stimulation side effect, the stimulation focusing performance must be ensured.
Because the target area of the mental diseases is usually positioned at a specific intracranial depth, and the intracranial biological tissues are complex, the conductivities and the magnetic conductivities of different biological tissues are low and are respectively unequal, the induced electric field generated in the stimulation process decays rapidly when longitudinally propagating in the cranium, and the effective induced electric field is difficult to reach the deep cranium. On the other hand, along with the increase of the stimulation depth, the induced electric field generated by the traditional stimulation coil is seriously dispersed, so that the stimulation coverage of the half brain or the whole brain is often caused, the stimulation depth and the stimulation focusing performance cannot be considered, and the requirement of deep brain stimulation is difficult to meet. For example, a splayed coil is the most common commercial transcranial magnetic stimulation coil on the market today that can generate an eddy current-shaped focused stimulation zone 1.5cm to 2cm below the scalp to achieve cortical excitability modulation, but the target zone for deep craniocerebral stimulation is typically located at a depth below the scalp of greater than 4cm, beyond the effective stimulation range of the splayed coil.
In order to further improve the stimulation depth of transcranial magnetic stimulation, researchers at present sequentially propose a plurality of deep brain stimulation coil structures such as biconical stimulation coils, H coils, concentric coils and the like to improve the stimulation depth, but the structures all sacrifice the stimulation focusing property, so that the tissues in a non-target area are exposed to stronger stimulation in a large area, and the risk of inducing stimulation side effects is increased. Meanwhile, due to the fact that a biological electromagnetic stimulation model is complex, the dominant analytic relation between stimulation current parameters and deep brain stimulation characteristics cannot be obtained through mathematical deduction, and multiple characteristic indexes for evaluating deep brain stimulation effects are mutually restricted, so that multi-objective optimization of the craniocerebral stimulation coil is difficult to achieve.
In conclusion, the stimulation coil is optimally designed to improve the deep stimulation effect of the biological cranium and the focusing stimulation is realized on the premise of ensuring the stimulation depth, so that the method has important significance for clinical treatment and scientific research of mental diseases.
Disclosure of Invention
The invention aims to provide a tangential surrounding type space array and a tangential surrounding type space array system for deep noninvasive focusing stimulation of cranium, which are used for solving the problem that the existing cranium electromagnetic stimulation technology cannot achieve both stimulation depth and stimulation focusing performance.
In order to achieve the above purpose, the present invention adopts the following technical scheme:
in a first aspect, a tangential surrounding spatial array for deep craniocerebral non-invasive focused stimulation is provided, comprising a plurality of tangential coils with the same geometric parameters for transverse surrounding of a human head, wherein the tangential coils refer to coil structures capable of being tangential to the scalp surface of the human head;
when the tangential surrounding type space array works, a plurality of stimulating currents which are in one-to-one correspondence with the tangential coils are input to the tangential coils, wherein the stimulating currents are used for generating a plurality of first induced electric field vectors with the characteristics of similar amplitude and smaller included angle at the deep part of the cranium through the tangential coils, and generating a plurality of second induced electric field vectors with the characteristics of larger amplitude difference and larger included angle at the shallow layer of the scalp.
Based on the above summary, a design scheme of a coil space array for deep non-invasive focusing stimulation of cranium is provided, namely, the design scheme comprises a plurality of tangential coils which are used for being transversely arranged around the head of a human body and have the same geometric parameters, wherein the tangential coils refer to a coil structure which can be tangential to the scalp surface of the head of the human body; when the coil space array works, a plurality of stimulation currents which are in one-to-one correspondence with the tangential coils are input to the tangential coils, wherein the stimulation currents are used for generating a plurality of first induction electric field vectors with the characteristics of similar amplitude and smaller included angle at the deep part of the cranium through the tangential coils, and generating a plurality of second induction electric field vectors with the characteristics of larger amplitude difference and larger included angle at the shallow part of the scalp, so that the superposition effect of the induction electric field at the deep part of the cranium can be enhanced, the stimulation depth is effectively improved, the purposes of spatially selective stimulation and improving the stimulation focusing are realized, the stimulation of biological tissues at the depth of more than 4 cm below the scalp can be facilitated, and the requirement of cranium stimulation on the stimulation depth is met.
In one possible design, the current magnitudes of the plurality of stimulation currents are determined as follows:
Determining a multidimensional decision variable i= { B 1 ,B 2 ,…,B m ,…,B M Establishing the tangential surrounding type space array and the three-dimensional finite element numerical model of the human head, wherein M represents the total current of the plurality of stimulating currents, M represents a positive integer less than or equal to M, B m A current magnitude variable representing an mth stimulating current of the plurality of stimulating currents, provided that 1kA is less than or equal to B m ≤5kA；
Assigning Initial values to the multidimensional decision variable I for a plurality of times under the constraint condition to form a current magnitude Initial value group initial_I= { I of the plurality of stimulating currents 1 ,I 2 ,…,I n ,…,I N Wherein N represents an initial value given total number of times, N represents a positive integer of N or less, I n A set of initial current values representing the plurality of stimulation currents obtained by applying the initial value n-th time;
leading the Initial value group of the current magnitude into the three-dimensional finite element numerical model for simulation operation, and obtaining N groups of deep craniocerebral stimulation characteristic index data corresponding to N groups of Initial values of the current magnitude in the Initial value group of the current magnitude, wherein each group of deep craniocerebral stimulation characteristic index data in the N groups of deep craniocerebral stimulation characteristic index data comprises simulation operation result values of at least one deep craniocerebral stimulation characteristic index;
Taking the N groups of initial values of current as input items and the N groups of deep brain stimulation characteristic index data as output items, performing rated verification modeling on artificial intelligent models based on a support vector machine, a K nearest neighbor method, a random gradient descent method, a multivariable linear regression, a multi-layer perceptron, a decision tree, a counter-propagating neural network or a radial basis function network to obtain a prediction model of each deep brain stimulation characteristic index in the at least one deep brain stimulation characteristic index and based on the multidimensional decision variable I;
taking a prediction model of each craniocerebral deep stimulation characteristic index and based on the multidimensional decision variable I as an optimization objective function, and carrying out multi-objective optimization by adopting an NSGA-II algorithm under the constraint condition to obtain an optimal solution of the multidimensional decision variable I;
and taking the optimal solution of the multi-dimensional decision variable I as the current magnitude of the plurality of stimulating currents.
In one possible design, the multi-dimensional decision variable I is given Initial values a plurality of times under the constraint condition, constituting a current magnitude Initial value set initial_i= { I for the plurality of stimulus currents 1 ,I 2 ,…,I n ,…,I N -comprising:
sampling the multi-dimensional decision variable I for multiple times by using Latin hypercube function under the constraint condition to form a current magnitude Initial value group initial_I= { I of the multiple stimulating currents 1 ,I 2 ,…,I n ,…,I N Wherein N represents an initial value given total number of times, N represents a positive integer of N or less, I n A set of initial values of current magnitudes representing the plurality of stimulation currents obtained by the nth-time application of the initial values.
In one possible design, the at least one deep cranium stimulation characteristic index includes any one of or any combination of a stimulation intensity, a focusing area and a longitudinal attenuation rate, wherein the stimulation intensity is a positive index represented by a maximum value of an induced electric field at an intracranial target region on an X test line and a Y test line, the focusing area is a negative index represented by an area formed by data points with the stimulation intensity greater than a stimulation threshold on an intracranial test plane, the longitudinal attenuation rate is another positive index represented by a ratio of an induced electric field amplitude at a deep cranium test target point on a Z test line to an induced electric field amplitude at a shallow scalp test target point on the Z test line, the X test line, the Y test line and the intracranial test plane are all located in an XYZ coordinate system with a scalp vertex coordinate origin, an X-axis positive direction in the XYZ coordinate system is a right direction of the human head, a Y-axis positive direction in the XYZ coordinate system is represented by x=0, and the x=0 in the z=l=0.
In one possible design, performing multi-objective optimization using NSGA-II algorithm under the constraint condition to obtain an optimal solution of the multi-dimensional decision variable I, including:
adopting NSGA-II algorithm to perform multi-objective optimization under the constraint condition;
judging whether the current evolution algebra in the NSGA-II algorithm exceeds a preset maximum allowable evolution algebra or not;
if yes, acquiring the optimal solution of the multidimensional decision variable I according to the current multi-objective optimization result, otherwise, enabling the current evolution algebra to be self-added by 1, and returning to the step of performing calibration verification modeling.
In one possible design, the tangential coil is composed of at least two longitudinally arranged coil units.
In one possible design, the tangential coil adopts a B-type coil including a current input terminal, a longitudinal lower coil unit, a longitudinal long side conductor, a longitudinal upper coil unit and a current output terminal, wherein the longitudinal lower coil unit adopts a fan-shaped structure made by winding from inside to outside, the longitudinal upper coil unit adopts a fan-shaped structure made by winding from outside to inside, the current input terminal, the longitudinal lower coil unit, the longitudinal long side conductor, the longitudinal upper coil unit and the current output terminal are electrically connected in sequence, and the longitudinal lower coil unit and the longitudinal upper coil unit have a space angle so that the longitudinal lower coil unit and the longitudinal upper coil unit can be tangent to the scalp surface of the human head, respectively.
In one possible design, the plurality of tangential coils includes at least two pairs of B-shaped coils, wherein each pair of B-shaped coils is arranged in a back-to-back arrangement with long sides thereof being closed when arranged laterally around the human head.
In a second aspect, a transcranial magnetic stimulation system is provided, which comprises a control module, a direct current power supply module, a charging switch and a stored energy stimulation circuit, wherein the stored energy stimulation circuit comprises a plurality of stimulation modules which are connected in parallel and have the same electrical structure;
the first output end of the control module is electrically connected with the controlled end of the charging switch and is used for outputting a first driving signal to the charging switch;
the direct-current power supply module is electrically connected with the energy storage stimulation circuit through the charging switch to form a direct-current charging loop;
the charging switch is used for switching on or switching off the direct-current charging loop according to the first driving signal;
the plurality of stimulation modules are in one-to-one correspondence with a plurality of tangential coils in a tangential circumferential spatial array as described in the first aspect or any of the possible designs of the first aspect and for deep non-invasive focused stimulation of the cranium, wherein each stimulation module of the plurality of stimulation modules comprises a corresponding said tangential coil.
In one possible design, the stimulation module further comprises an energy storage capacitor, a voltage detection unit, a current detection unit, a precision potentiometer and a discharge switch, wherein a high potential end of the energy storage capacitor is electrically connected with a current input end of the tangential coil through the precision potentiometer and the discharge switch, and a current output end of the tangential coil is electrically connected with a low potential end of the energy storage capacitor through the current detection unit to form a stimulation current loop;
the voltage detection unit is connected in parallel with two ends of the energy storage capacitor and is used for monitoring voltage amplitude values of the two ends of the energy storage capacitor and taking a detected voltage signal as one path of input signal of the control module;
the current detection unit is used for taking the detected current signal as another path of input signal of the control module;
the controlled end of the discharge switch is electrically connected with the second output end of the control module and is used for switching on or switching off the stimulation current loop according to the second driving signal after receiving the second driving signal from the control module;
the controlled end of the precision potentiometer is electrically connected with the third output end of the control module and is used for adjusting the current in the stimulation current loop according to the current size adjusting signal after receiving the current size adjusting signal which is obtained from the control module and is based on the two paths of input signals.
The beneficial effect of above-mentioned scheme:
(1) The invention provides a coil space array design scheme for deep craniocerebral noninvasive focusing stimulation, which comprises a plurality of tangential coils which are used for transversely surrounding the head of a human body and have the same geometric parameters, wherein the tangential coils are coil structures which can be tangent to the scalp surface of the head of the human body; when the coil space array works, a plurality of stimulation currents which are in one-to-one correspondence with the tangential coils are input to the tangential coils, wherein the stimulation currents are used for generating a plurality of first induction electric field vectors with the characteristics of similar amplitude and smaller included angle at the deep part of the cranium through the tangential coils, and generating a plurality of second induction electric field vectors with the characteristics of larger amplitude difference and larger included angle at the shallow part of the scalp, so that the superposition effect of the induction electric field at the deep part of the cranium can be enhanced, the stimulation depth can be effectively improved, the purposes of spatially selective stimulation and improving the stimulation focusing are realized, the stimulation of biological tissues at the depth of more than 4 cm below the scalp can be facilitated, and the requirement of cranium stimulation on the stimulation depth can be met;
(2) The method also provides an in-array stimulation current parameter configuration scheme based on NSGA-II algorithm, which can acquire the optimal in-array stimulation current parameters, realize the purpose of global optimization of the space array, and further solve the problem of high difficulty in optimizing the stimulation array caused by the fact that the dominant analytic relationship between the stimulation current parameters and deep brain stimulation characteristics cannot be directly acquired through mathematical derivation;
(3) Compared with the traditional splayed coil array, the device can increase the stimulation intensity by 4.79 times, reduce the focusing area by 78.5 percent and increase the longitudinal attenuation rate by 3.76 times, thereby improving the stimulation depth and the focusing performance and obviously enhancing the focusing stimulation effect at the deep part of the cranium;
(4) The method can keep the advantages of noninvasive biological magnetic stimulation and no need of operation, does not need to physically move the stimulation coil in the stimulation process, is friendly to clinical operation and has low economic cost.
Drawings
In order to more clearly illustrate the embodiments of the invention or the technical solutions in the prior art, the drawings that are required in the embodiments or the description of the prior art will be briefly described, it being obvious that the drawings in the following description are only some embodiments of the invention, and that other drawings may be obtained according to these drawings without inventive effort for a person skilled in the art.
Fig. 1 is a schematic diagram of an arrangement relationship between a tangential surrounding type space array and a human head according to an embodiment of the present application, where fig. 1 (a) shows a schematic perspective structure of the arrangement relationship, fig. 1 (b) shows a schematic top view structure of the arrangement relationship, fig. 1 (c) shows a schematic side view structure of the arrangement relationship, and fig. 1 (d) shows a schematic front view structure of the arrangement relationship.
Fig. 2 is a schematic diagram of a winding structure of 8B-type coils according to an embodiment of the present application.
Fig. 3 is a schematic diagram of a flow chart of determining the current levels of a plurality of stimulus currents according to an embodiment of the present application.
Fig. 4 is a schematic diagram showing the spatial positional relationship among XYZ test lines, intracranial test planes, and scalp vertices provided in an embodiment of the present application.
Fig. 5 is a diagram of an example of a prediction effect of an artificial intelligence model structure based on a back propagation neural network and a three-index prediction model according to an embodiment of the present application, where fig. 5 (a) shows the artificial intelligence model structure based on the back propagation neural network, fig. 5 (b) shows an example of a prediction effect of a prediction model for a stimulus intensity index, fig. 5 (c) shows an example of a prediction effect of a prediction model for a focus area index, and fig. 5 (d) shows an example of a prediction effect of a prediction model for a longitudinal decay rate index.
Fig. 6 is a diagram illustrating distribution of induced electric fields generated in deep cranium by a tangential surrounding type spatial array according to an embodiment of the present application.
Fig. 7 is a diagram illustrating distribution of an induced electric field generated in a deep cranium by a conventional splayed coil array according to an embodiment of the present application.
Fig. 8 is a schematic structural diagram of a transcranial magnetic stimulation system according to an embodiment of the present application.
Fig. 9 is a schematic structural diagram of a stimulation module in a transcranial magnetic stimulation system according to an embodiment of the present application.
Detailed Description
In order to more clearly illustrate the embodiments of the present application or the technical solutions in the prior art, the present application will be briefly described below with reference to the accompanying drawings and the description of the embodiments or the prior art, and it is obvious that the following description of the structure of the drawings is only some embodiments of the present application, and other drawings can be obtained according to these drawings without inventive effort to a person skilled in the art. It should be noted that the description of these examples is for aiding in understanding the present application, but is not intended to limit the present application.
It should be understood that although the terms first and second, etc. may be used herein to describe various objects, these objects should not be limited by these terms. These terms are only used to distinguish one object from another. For example, a first object may be referred to as a second object, and similarly a second object may be referred to as a first object, without departing from the scope of example embodiments of the application.
It should be understood that for the term "and/or" that may appear herein, it is merely one association relationship that describes an associated object, meaning that there may be three relationships, e.g., a and/or B, may represent: three cases of A alone, B alone or both A and B exist; as another example, A, B and/or C, can represent the presence of any one of A, B and C or any combination thereof; for the term "/and" that may appear herein, which is descriptive of another associative object relationship, it means that there may be two relationships, e.g., a/and B, it may be expressed that: the two cases of A and B exist independently or simultaneously; in addition, for the character "/" that may appear herein, it is generally indicated that the context associated object is an "or" relationship.
Examples:
as shown in fig. 1, the tangential surrounding type space array provided in the first aspect of the present embodiment and used for deep craniocerebral non-invasive focusing stimulation includes, but is not limited to, a plurality of tangential coils with the same geometric parameters and used for being transversely arranged around the head of a human body, wherein the tangential coils refer to a coil structure capable of being tangential to the scalp surface of the head of the human body; when the tangential surrounding type space array works, a plurality of stimulating currents which are in one-to-one correspondence with the tangential coils are input to the tangential coils, wherein the stimulating currents are used for generating a plurality of first induced electric field vectors with the characteristics of similar amplitude and smaller included angle at the deep part of the cranium through the tangential coils, and generating a plurality of second induced electric field vectors with the characteristics of larger amplitude difference and larger included angle at the shallow layer of the scalp.
As shown in fig. 1, in the specific structure of the tangential surrounding type space array, each tangential coil of the plurality of tangential coils is used for introducing a corresponding stimulation current so as to generate a corresponding induced electric field vector. Because the tangential coil can be tangent to the scalp surface of the human head, the accumulation of intracranial non-longitudinal induction electric field components can be reduced, and the focusing property of deep brain stimulation can be improved. Because the plurality of tangent coils are transversely arranged around the head of the human body, the coil centers and the deep craniocerebral centers can be basically positioned at the same height, thereby being further beneficial to guiding electromagnetic energy to the deep craniocerebral region and improving the deep brain stimulation effect. Meanwhile, when the tangential surrounding type space array works, the plurality of stimulation currents are input to the plurality of tangential coils, the plurality of first induction electric field vectors which have the characteristics of similar amplitude and smaller included angle are generated in the deep part of the cranium, so that the longitudinal induction electric field synthesized in the deep part of the cranium is larger, the purpose of enhancing the deep induction electric field of the cranium is realized, and the plurality of second induction electric field vectors which have the characteristics of larger amplitude difference and larger included angle are generated in the shallow layer of the scalp, so that the longitudinal induction electric field synthesized in the shallow layer of the scalp is smaller, and the purpose of weakening the induction electric field of the shallow surface layer is realized. Through the structural design of the tangential surrounding type space array and the plurality of stimulation currents, the superposition effect of the induction electric field in the deep region of the cranium can be enhanced, the stimulation depth is effectively improved, the purposes of spatially selective stimulation and improving the stimulation focusing are achieved, further, the stimulation of biological tissues below the scalp at the depth of more than 4 cm can be facilitated, and the requirement of cranium stimulation on the stimulation depth is met.
Preferably, the tangential coil is composed of at least two longitudinally arranged coil units, so as to promote geometric flexibility, even if the upper coil unit and the lower coil unit can form various space included angles, the tangential coil is more fit with the scalp structure of a human body, electromagnetic energy loss in the space is reduced, and the stimulation focusing performance is further improved. Specifically, as shown in fig. 1 and 2, taking a tangential coil located on the left side of the forehead as an example, the tangential coil adopts a B-type coil including, but not limited to, a current input terminal 13, a longitudinal lower coil unit 14, a longitudinal long side conductor 15, a longitudinal upper coil unit 16 and a current output terminal 17, wherein the longitudinal lower coil unit 14 adopts a fan-shaped structure manufactured by winding from inside to outside, the longitudinal upper coil unit 16 adopts a fan-shaped structure manufactured by winding from outside to inside, and the current input terminal 13, the longitudinal lower coil unit 14, the longitudinal long side conductor 15, the longitudinal upper coil unit 16 and the current output terminal 17 are electrically connected in sequence, and the longitudinal lower coil unit 14 has a spatial angle with the longitudinal upper coil unit 16, so that the longitudinal lower coil unit 14 and the longitudinal upper coil unit 16 can be tangent to the scalp surface of the human head, respectively. As shown in fig. 1, the upper and lower parts of the two B-type coils (1, 8) located on the left side of the forehead and on the right side of the forehead form an included angle 9; the upper and lower parts of the two B-shaped coils (2, 3) positioned in front of the right ear and behind the right ear form an included angle 10; the upper and lower parts of the two B-shaped coils (4, 5) positioned on the left side of the rear pillow part and on the right side of the rear pillow part form an included angle 11; the upper and lower parts of the two B-shaped coils (6, 7) located behind the left ear and in front of the left ear form an included angle 12, so that the structure can be more in accordance with the ergonomics. In addition, as shown in fig. 2, the component numbers of the B-type coils 2 to 8 may be derived from the component numbers of the B-type coil 1, and will not be described herein.
Further preferably, the plurality of tangential coils includes at least two pairs of B-shaped coils, wherein each pair of B-shaped coils is arranged in a back-to-back manner with long sides close to each other when being arranged transversely around the head of the human body. As shown in fig. 1 and 2, the two B-type coils (1, 8) on the left side of the forehead and on the right side of the forehead are respectively tangent to the scalp longitudinally, and the two longitudinal long-side conductors (15, 20) are close to each other and are in a back-to-back arrangement at the forehead of the head, thus forming forehead position stimulation. As shown in FIG. 2, the direction of the stimulating current of all the B-type coils is the same from bottom to top, so that the induced electric field generated by the coils below the long-side conductors is the same (taking the B-type coils positioned on the left side of the forehead as an example, the induced magnetic field direction is the direction that the coil center vertically passes out of the paper surface, so that the induced magnetic field below the coils is enhanced, and the induced magnetic field in the direction is weakened according to Lenz theorem, so that the induced electric field is clockwise, and similarly, the induced electric field is anticlockwise when the stimulating current direction of the B-type coils positioned on the right side of the forehead is clockwise, so that when the two B-type coils are positioned back to back, the middle tangential position and the induced electric field direction are consistent), further, the intracranial longitudinal induced electric field is effectively overlapped, so that the stimulation intensity is ensured to be enhanced, and finally, an obvious target area is formed below the center of the B-type coils. In addition, as shown in fig. 1, for example, the plurality of tangential coils includes four pairs of the B-type coils (1, 8) uniformly distributed in four directions of front, rear, left and right with the center of the head as an origin, that is, two B-type coils (2, 3) located on the left side of the forehead and on the right side of the forehead, two B-type coils (4, 5) located in front of the right ear and behind the right ear, two B-type coils (4, 5) located on the left side of the rear pillow and on the right side of the rear pillow, and two B-type coils (6, 7) located behind the left ear and in front of the left ear.
Considering that after the geometry of the tangential surrounding type spatial array and the position of the head relative to the human body are determined, the deep brain stimulation effect is also determined by the configuration result of the intra-array stimulation current parameters (i.e. the current magnitudes of the multiple stimulation currents), but the explicit analysis relation between the intra-array stimulation current parameters and the deep brain stimulation characteristics cannot be directly obtained through mathematical deduction, which results in great difficulty in optimizing the stimulation array (i.e. the explicit analysis relation between the stimulation current parameters and the deep brain stimulation characteristics cannot be obtained through mathematical deduction due to the complex biological electromagnetic stimulation model, and the multiple characteristic indexes for evaluating the deep brain stimulation effect have mutual restriction, which results in great difficulty in optimizing the array due to the multiple targets of the stimulation coils).
S1, determining a multidimensional decision variable I= { B 1 ,B 2 ,…,B m ,…,B M -and establishing said tangentially-surrounding spatial array and saidThe three-dimensional finite element numerical model of the human head, wherein M represents the total current of the plurality of stimulating currents, M represents a positive integer less than or equal to M, B m A current magnitude variable representing an mth stimulating current of the plurality of stimulating currents, provided that 1kA is less than or equal to B m ≤5kA。
In the step S1, the multi-dimensional decision variable I may be determined in particular by analyzing the geometry of the tangentially-and-circumferentially-spaced array and checking the total number of intra-array coils. The three-dimensional finite element numerical model is a three-dimensional finite element model, can be conventionally established by using the existing finite element analysis method, and is required to be converted into a script file which can be identified by Matlab software in order to facilitate the subsequent simulation operation application in the Matlab software. In addition, kA represents a current magnitude unit and is kiloamperes.
S2, giving Initial values to the multidimensional decision variable I for a plurality of times under the constraint condition to form a current magnitude Initial value group initial_I= { I of the plurality of stimulating currents 1 ,I 2 ,…,I n ,…,I N Wherein N represents an initial value given total number of times, N represents a positive integer of N or less, I n A set of initial values of current magnitudes representing the plurality of stimulation currents obtained by the nth-time application of the initial values.
In the step S2, specifically, the multi-dimensional decision variable I is sampled multiple times under the constraint condition by using a latin hypercube function to form a current magnitude Initial value group initial_i= { I of the multiple stimulus currents 1 ,I 2 ,…,I n ,…,I N Wherein N represents an initial value given total number of times, N represents a positive integer of N or less, I n A set of initial values of current magnitudes representing the plurality of stimulation currents obtained by the nth-time application of the initial values. The latin hypercube function is the existing function, and the specific way to sample the initial value is also the existing conventional way.
S3, importing the Initial current value set initial_I into the three-dimensional finite element numerical model for simulation operation, and obtaining N groups of deep craniocerebral stimulation characteristic index data corresponding to N groups of Initial current values in the Initial current value set initial_I one by one, wherein each group of deep craniocerebral stimulation characteristic index data in the N groups of deep craniocerebral stimulation characteristic index data comprises simulation operation result values of at least one deep craniocerebral stimulation characteristic index.
In the step S3, the at least one deep brain stimulation characteristic index is used to analyze three-dimensional spatial distribution characteristics of the intracranial induced electric field so as to verify the deep brain stimulation effect of the tangential surrounding type spatial array. Specifically, the at least one deep craniocerebral stimulation characteristic index includes, but is not limited to, any one of or any combination of a stimulation intensity, a focusing area and a longitudinal attenuation rate, wherein the stimulation intensity is a positive index represented by using an induced electric field maximum value of an intracranial target region on an X test line and a Y test line, the focusing area is a negative index represented by using an area formed by data points with the stimulation intensity greater than a stimulation threshold on an intracranial test plane, the longitudinal attenuation rate is another positive index represented by using a ratio of an induced electric field amplitude at a deep craniocerebral test target point on a Z test line to an induced electric field amplitude at a shallow scalp test target point on the Z test line, the X test line, the Y test line, the Z test line and the intracranial test plane are all located in an XYZ coordinate system with a vertex as a coordinate origin, an X-axis positive direction in the XYZ coordinate system is a right direction of the human head, a Y-axis positive direction in the XYZ coordinate system is a front of the XYZ coordinate system, the X-axis is a Z-axis is represented by using a z=0, and the z=0 to represent the human head from the x=0. The spatial positional relationship of the X test line 53, the Y test line 54, the Z test line 55, and the intracranial test plane 56 is shown in FIG. 4. Furthermore, the simulation operations may be performed specifically in Matlab software.
S4, taking the initial values of the N groups of currents as input items and taking the data of the N groups of deep brain stimulation characteristic indexes as output items, performing calibration verification modeling on artificial intelligent models based on support vector machines, K nearest neighbor methods, random gradient descent methods, multivariable linear regression, multi-layer perceptrons, decision trees, back propagation neural networks or radial basis function networks and the like, and obtaining a prediction model of each deep brain stimulation characteristic index in the at least one deep brain stimulation characteristic index and based on the multidimensional decision variable I.
In the step S4, the support vector machine, the K nearest neighbor method, the random gradient descent method, the multivariate linear regression, the multi-layer perceptron, the decision tree, the back propagation neural network and the radial basis function network are all common schemes in the existing artificial intelligence method; taking Back Propagation (BP) neural network as an example, it is a multi-layer feedforward neural network (i.e. composed of 3 parts such as input layer, hidden layer and output layer) which realizes BP neural network algorithm (i.e. intelligent algorithm formed by simulating human brain biological organization form) and trains according to error Back Propagation algorithm, the basic idea is gradient descent method, which uses error feedback to repeatedly learn training to make the error of the actual output value and the expected output value of the network minimum), it has advantages of simple model and low operation, it can fit the internal relation between decision variable and objective function by learning various training sets to solve the problem of limited fitting ability of dominant function, it is the most widely applied neural network model. The specific process of calibration verification modeling comprises a calibration process and a checking process of a model, namely, a simulation result and actual measurement data of the model are compared, and model parameters are adjusted according to the comparison result, so that the simulation result is matched with the actual process, and a prediction model of each deep craniocerebral stimulation characteristic index and based on the multidimensional decision variable I can be obtained through a conventional calibration verification modeling mode. For example, using an artificial intelligence model based on the back propagation neural network as shown in FIG. 5 (a), there are M input nodes at the input layer to correspond one-to-one to the multi-dimensional decision variable I, and 3 at the output layer Output nodes so as to correspond the stimulus intensity, the focusing area and the longitudinal attenuation rate one by one, and further set training times net.trainParam. Epochs=1000, learning rates net.trainParam. Lr=0.01, training minimum errors net.trainParam. Gold=0.000001 in the BP neural network, the number of sets of training data is TrainN, the number of test data sets is TestN, and the requirements are satisfied: trainN+TestN=N=50; a predictive model E of the stimulus intensity and based on the multidimensional decision variable I when the test data set number testn=5 BP (I) The comparison between the predicted data and the actual data of (a) may be as shown in fig. 5 (b): correlation coefficient R between two data 2 About 0.98; a predictive model S of the focal area and based on the multi-dimensional decision variable I when the test dataset number testn=5 70,BP (I) The comparison between the predicted data and the actual data of (c) can be as shown in fig. 5 (c): correlation coefficient R between two data 2 About 0.96; a predictive model delta of the longitudinal decay rate and based on the multi-dimensional decision variable I when the test data set number testn=5 BP (I) The comparison between the predicted data and the actual data of (a) can be as shown in fig. 5 (d): correlation coefficient R between two data 2 About 0.95; thus, it can be shown that three prediction models E with higher reliability can be obtained by carrying out calibration verification modeling on the artificial intelligence model based on the back propagation neural network BP (I)、S 70,BP (I) And delta BP (I)。
S5, taking the prediction model of each craniocerebral deep stimulation characteristic index and based on the multidimensional decision variable I as an optimization objective function, and carrying out multi-objective optimization by adopting an NSGA-II algorithm under the constraint condition to obtain the optimal solution of the multidimensional decision variable I.
In the step S5, since the stimulus intensity is a positive index, the corresponding optimization direction is a search maximum value: max (E) BP (I) A) is provided; since the focusing area is a negative index, the corresponding optimization direction is the search minimum value: min (S) 70,BP (I) A) is provided; since the longitudinal attenuation rate is another forward index, the corresponding optimization direction is also the search maximum value: max (delta) BP (I))。The NSGA-II (Non-dominated Sorting Genetic Algorithm-II, non-dominant order genetic algorithm second generation) algorithm is one of the most popular multi-objective genetic algorithms, a rapid Non-dominant order algorithm is adopted (namely, the general flow is that a population is initialized, non-dominant order is carried out on the population, a generation of offspring population is obtained through selection, crossing and mutation of the genetic algorithm, the evolution algebra is 1 at the moment, rapid Non-dominant order is carried out and the crowding degree of each Non-dominant layer individual is calculated from the evolution algebra of 2 to form a new father population, the new offspring population is generated through selection, crossing and mutation of the genetic algorithm again), the calculation complexity is greatly reduced compared with that of NSGA (Non-dominated Sorting Genetic Algorithm, non-dominant order genetic algorithm), the operation speed and the robustness of the algorithm are improved, the method is suitable for solving the problem of multi-objective optimization of a space array, and therefore, the optimal solution of the multi-dimensional decision variable I can be obtained through multi-objective optimization through adopting the NSGA-II algorithm under the constraint condition. Specifically, the multi-objective optimization is performed by adopting an NSGA-II algorithm under the constraint condition to obtain the optimal solution of the multi-dimensional decision variable I, including but not limited to: adopting NSGA-II algorithm to perform multi-objective optimization under the constraint condition; judging whether the current evolution algebra in the NSGA-II algorithm exceeds a preset maximum allowable evolution algebra or not; if yes, acquiring the optimal solution of the multi-dimensional decision variable I according to the current multi-objective optimization result, otherwise, adding 1 to the current evolution algebra, and returning to the step of performing calibration verification modeling (namely returning to execute the step S4).
S6, taking the optimal solution of the multi-dimensional decision variable I as the current magnitude of the plurality of stimulating currents.
Therefore, based on the configuration scheme of the stimulation current parameters in the array described in the steps S1 to S6, the optimal stimulation current parameters in the array can be obtained, and the purpose of global optimization of the space array is achieved.
The embodiment is based on the structural design of the tangential surrounding type space array and the configuration scheme of the stimulating current parameters in the array, and the following comparative tests (A) and (B) are also performed:
(A) The length of the long side of the coil B is 40mm, the wire diameter is 3mm×4mm, the total number of turns k=16, then the tangential surrounding type space array of this embodiment is obtained based on the B-type coil construction (i.e., a plurality of tangential coils includes four pairs of the B-type coils uniformly distributed in four directions around the center of the head as the origin), and the scalp 57 and the brain grey matter 58 are modeled to form a human head model, and the space array optimal stimulation currents {2028a,2426a,4771a, 45700 a,1438a,3581a,1731a,2442a } are also obtained by using the intra-array stimulation current parameter configuration scheme. The distribution of induced electric fields generated by the tangentially-encircling spatial array at the intracranial target plane is shown in fig. 6 (the solid lines with arrows in the figure represent the spatially induced electric field vectors). As can be seen from fig. 6, the induced electric field generated by the tangential circumferential space array can form a distinct focal zone 59 in the deep cranium; and the stimulation intensity generated by the tangential surrounding type space array at the stimulation depth depth=10cm is 11.57V/m, and the focusing area is 23.67cm is obtained through finite element numerical analysis 2 And a longitudinal decay rate of 2.43;
(B) Taking out the outer diameter R of a single round coil 1 The wire diameter was 3mm×4mm and the total number of turns was 16, constituting a conventional splayed coil array as a control array, and also modeling the scalp 57 and the brain gray matter 58, constituting a human head model. The conventional splayed coil array is equal to the tangential wrap-around spatial array in joule loss when the stimulation currents in each single circular coil of the array are equal and are both 3734A. At this time, the distribution of the induced electric field generated by the conventional splayed coil array on the intracranial target plane 56 is shown in fig. 7 (the solid line with arrow in the figure indicates the space induced electric field vector), and the generated induced electric field focusing area 60 is close to the vertex of the scalp and is positioned on the shallow scalp layer (as shown by the dotted line box in the figure), so that the deep cranium cannot be reached; and the stimulation intensity generated by the traditional splayed coil array at the stimulation depth depth=10cm is 2V/m, and the focusing area is 110cm is obtained through finite element numerical analysis 2 And a longitudinal decay rate of 0.51.
Based on the results of the comparison tests (a) and (B), compared with the conventional splayed coil array, the tangential surrounding type space array provided by the embodiment has more ideal distribution form of the induced electric field generated in the deep part of the cranium, namely, the tangential surrounding type space array provided by the embodiment can generate an obvious focusing stimulation area at the stimulation depth=10cm, and compared with the conventional splayed coil array, the stimulation intensity can be improved by 4.79 times, the focusing area can be reduced by 78.5%, and the longitudinal attenuation rate can be improved by 3.76 times, so that the improvement of the stimulation depth and the focusing performance can be considered, and the focusing stimulation effect in the deep part of the cranium can be obviously enhanced.
As shown in fig. 8, a second aspect of the present embodiment provides a transcranial magnetic stimulation system using the tangential circumferential space array of the first aspect, including but not limited to a control module, a dc power module, a charging switch, and a tank stimulation circuit, wherein the tank stimulation circuit includes a plurality of stimulation modules connected in parallel and having the same electrical structure; the first output end of the control module is electrically connected with the controlled end of the charging switch and is used for outputting a first driving signal to the charging switch; the direct-current power supply module is electrically connected with the energy storage stimulation circuit through the charging switch to form a direct-current charging loop; the charging switch is used for switching on or switching off the direct-current charging loop according to the first driving signal; the plurality of stimulation modules are in one-to-one correspondence with a plurality of tangential coils in the tangential circumferential spatial array for deep craniocerebral non-invasive focused stimulation as described in the first aspect, wherein each stimulation module of the plurality of stimulation modules comprises a corresponding said tangential coil.
As shown in fig. 8, in a specific structure of the transcranial magnetic stimulation system, the control module is used as a system control center, and may, but is not limited to, control on or off of the direct current charging loop, and may be specifically implemented by a microcontroller of the STM32F105 series. The dc power module is configured to provide high-voltage dc power, as shown in fig. 8, and may specifically but not limited to include a power frequency power supply (which is configured to provide 220V and 50Hz power frequency mains supply), a rectifying and filtering circuit, an inverter circuit, a boost circuit, a rectifying circuit, and the like, which are electrically connected in sequence. The charging switch can be realized by adopting a conventional electric control switch. The plurality of stimulation modules are used for tangentially inputting the plurality of stimulation currents to the plurality of tangential directions so as to realize transcranial magnetic stimulation effects of the tangential surrounding type space array; as shown in fig. 9, the stimulation module specifically further includes, but is not limited to, an energy storage capacitor, a voltage detection unit, a current detection unit, a precision potentiometer and a discharge switch, wherein a high potential end of the energy storage capacitor is electrically connected with a current input end of the tangential coil through the precision potentiometer and the discharge switch, and a current output end of the tangential coil is electrically connected with a low potential end of the energy storage capacitor through the current detection unit to form a stimulation current loop; the voltage detection unit is connected in parallel with two ends of the energy storage capacitor and is used for monitoring voltage amplitude values of the two ends of the energy storage capacitor and taking a detected voltage signal as one path of input signal of the control module; the current detection unit is used for taking the detected current signal as another path of input signal of the control module; the controlled end of the discharge switch is electrically connected with the second output end of the control module and is used for switching on or switching off the stimulation current loop according to the second driving signal after receiving the second driving signal from the control module; the controlled end of the precision potentiometer is electrically connected with the third output end of the control module and is used for adjusting the current in the stimulation current loop according to the current size adjusting signal after receiving the current size adjusting signal which is obtained from the control module and is based on the two paths of input signals. In addition, the energy storage capacitor, the voltage detection unit, the current detection unit, the precision potentiometer and the discharge switch can be realized by adopting the existing devices.
The working process, working details and technical effects of the foregoing system provided in the second aspect of the present embodiment may refer to the tangential surrounding space array described in the first aspect, which are not described herein again.
Finally, it should be noted that: the foregoing description is only of the preferred embodiments of the invention and is not intended to limit the scope of the invention. Any modification, equivalent replacement, improvement, etc. made within the spirit and principle of the present invention should be included in the protection scope of the present invention.
Claims (7)
1. A tangential surrounding type space array for deep non-invasive focusing stimulation of cranium, which is characterized by comprising a plurality of tangential coils which are used for transversely surrounding the head of a human body and have the same geometric parameters, wherein the tangential coils are coil structures which can be tangential to the scalp surface of the head of the human body;
when the tangential surrounding type space array works, a plurality of stimulating currents which are in one-to-one correspondence with the tangential coils are input to the tangential coils, wherein the stimulating currents are used for generating a plurality of first induced electric field vectors with the characteristics of similar amplitude and smaller included angle at the deep part of the cranium through the tangential coils, and generating a plurality of second induced electric field vectors with the characteristics of larger amplitude difference and larger included angle at the shallow part of the scalp;
The tangential coil adopts a B-type coil comprising a current input terminal (13), a longitudinal lower coil unit (14), a longitudinal long-side conductor (15), a longitudinal upper coil unit (16) and a current output terminal (17), wherein the longitudinal lower coil unit (14) adopts a fan-shaped structure manufactured by a winding mode from inside to outside, the longitudinal upper coil unit (16) adopts a fan-shaped structure manufactured by a winding mode from outside to inside, and the current input terminal (13), the longitudinal lower coil unit (14), the longitudinal long-side conductor (15), the longitudinal upper coil unit (16) and the current output terminal (17) are electrically connected in sequence, and the longitudinal lower coil unit (14) and the longitudinal upper coil unit (16) have a space included angle, so that the longitudinal lower coil unit (14) and the longitudinal upper coil unit (16) can be respectively tangent with the surface of the head of a human body;
the tangential coils comprise at least two pairs of B-shaped coils, wherein each pair of B-shaped coils adopts a mode of long-side close and back-to-back arrangement when being transversely arranged around the head of the human body;
the current magnitudes of the plurality of stimulation currents are determined as follows:
Determining a multidimensional decision variable i= { B 1 ,B 2 ,…,B m ,…,B M Establishing the tangential surrounding type space array and the three-dimensional finite element numerical model of the human head, wherein M represents the total current of the plurality of stimulating currents, M represents a positive integer less than or equal to M, B m A current magnitude variable representing an mth stimulating current of the plurality of stimulating currents, provided that 1kA is less than or equal to B m ≤5kA；
Assigning Initial values to the multidimensional decision variable I for a plurality of times under the constraint condition to form a current magnitude Initial value group initial_I= { I of the plurality of stimulating currents 1 ,I 2 ,…,I n ,…,I N Wherein N represents an initial value given total number of times, N represents a positive integer of N or less, I n A set of initial current values representing the plurality of stimulation currents obtained by applying the initial value n-th time;
leading the Initial value group of the current magnitude into the three-dimensional finite element numerical model for simulation operation, and obtaining N groups of deep craniocerebral stimulation characteristic index data corresponding to N groups of Initial values of the current magnitude in the Initial value group of the current magnitude, wherein each group of deep craniocerebral stimulation characteristic index data in the N groups of deep craniocerebral stimulation characteristic index data comprises simulation operation result values of at least one deep craniocerebral stimulation characteristic index;
Taking the N groups of initial values of current as input items and the N groups of deep brain stimulation characteristic index data as output items, performing rated verification modeling on artificial intelligent models based on a support vector machine, a K nearest neighbor method, a random gradient descent method, a multivariable linear regression, a multi-layer perceptron, a decision tree, a counter-propagating neural network or a radial basis function network to obtain a prediction model of each deep brain stimulation characteristic index in the at least one deep brain stimulation characteristic index and based on the multidimensional decision variable I;
taking a prediction model of each craniocerebral deep stimulation characteristic index and based on the multidimensional decision variable I as an optimization objective function, and carrying out multi-objective optimization by adopting an NSGA-II algorithm under the constraint condition to obtain an optimal solution of the multidimensional decision variable I;
and taking the optimal solution of the multi-dimensional decision variable I as the current magnitude of the plurality of stimulating currents.
2. The tangential circumferential space array of claim 1, wherein said multi-dimensional decision variable I is given Initial values a plurality of times under said constraint, constituting a set of Initial values of current magnitude of said plurality of stimulus currents, initial_i= { I 1 ,I 2 ,…,I n ,…,I N -comprising:
sampling the multi-dimensional decision variable I for multiple times by using Latin hypercube function under the constraint condition to form a current magnitude Initial value group initial_I= { I of the multiple stimulating currents 1 ,I 2 ,…,I n ,…,I N Wherein N represents an initial value given total number of times, N represents a positive integer of N or less, I n A set of initial values of current magnitudes representing the plurality of stimulation currents obtained by the nth-time application of the initial values.
3. The tangential circumferential spatial array of claim 1, wherein the at least one deep brain stimulation characteristic index comprises any one or any combination of a stimulation intensity, a focal area and a longitudinal decay rate, wherein the stimulation intensity is a positive index represented by an induced electric field maximum at an intracranial target region on an X test line and a Y test line, the focal area is a negative index represented by an area formed by data points with a stimulation intensity greater than a stimulation threshold on an intracranial test plane, the longitudinal decay rate is another positive index represented by a ratio of an induced electric field amplitude at a deep brain test target point on a Z test line to an induced electric field amplitude at a shallow scalp test target point on the Z test line, the X test line, the Y test line, the Z test line and the Y test plane are all located in an XYZ coordinate system with a scalp vertex as a coordinate origin, an X-axis positive direction in the XYZ coordinate system is a right side of the human head coordinate, the Y-axis is a XYZ-axis in the XYZ coordinate system is a Y = 0, and a Z = X = 0, and the X = L = X is represented by a positive coordinate system from the human head.
4. The tangential wrap-around spatial array of claim 1, wherein performing multi-objective optimization using NSGA-II algorithm under the constraint conditions to obtain an optimal solution for the multi-dimensional decision variable I comprises:
adopting NSGA-II algorithm to perform multi-objective optimization under the constraint condition;
judging whether the current evolution algebra in the NSGA-II algorithm exceeds a preset maximum allowable evolution algebra or not;
if yes, acquiring the optimal solution of the multidimensional decision variable I according to the current multi-objective optimization result, otherwise, enabling the current evolution algebra to be self-added by 1, and returning to the step of performing calibration verification modeling.
5. The tangential circumferential space array of claim 1, wherein the tangential coils are comprised of at least two longitudinally aligned coil units.
6. The transcranial magnetic stimulation system is characterized by comprising a control module, a direct-current power supply module, a charging switch and an energy storage stimulation circuit, wherein the energy storage stimulation circuit comprises a plurality of stimulation modules which are connected in parallel and have the same electrical structure;
the first output end of the control module is electrically connected with the controlled end of the charging switch and is used for outputting a first driving signal to the charging switch;
The direct-current power supply module is electrically connected with the energy storage stimulation circuit through the charging switch to form a direct-current charging loop;
the charging switch is used for switching on or switching off the direct-current charging loop according to the first driving signal;
the plurality of stimulation modules are in one-to-one correspondence with a plurality of tangential coils in the tangential circumferential spatial array for deep non-invasive focused stimulation of the cranium of any one of claims 1-5, wherein each stimulation module of the plurality of stimulation modules includes a corresponding tangential coil.
7. The transcranial magnetic stimulation system according to claim 6, wherein the stimulation module further comprises an energy storage capacitor, a voltage detection unit, a current detection unit, a precision potentiometer and a discharge switch, wherein a high potential end of the energy storage capacitor is electrically connected with a current input end of the tangential coil through the precision potentiometer and the discharge switch, and a current output end of the tangential coil is electrically connected with a low potential end of the energy storage capacitor through the current detection unit to form a stimulation current loop;
the voltage detection unit is connected in parallel with two ends of the energy storage capacitor and is used for monitoring voltage amplitude values of the two ends of the energy storage capacitor and taking a detected voltage signal as one path of input signal of the control module;
The current detection unit is used for taking the detected current signal as another path of input signal of the control module;
the controlled end of the discharge switch is electrically connected with the second output end of the control module and is used for switching on or switching off the stimulation current loop according to the second driving signal after receiving the second driving signal from the control module;
the controlled end of the precision potentiometer is electrically connected with the third output end of the control module and is used for adjusting the current in the stimulation current loop according to the current size adjusting signal after receiving the current size adjusting signal which is obtained from the control module and is based on the two paths of input signals.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202211400947.2A CN115887932B (en) | 2022-11-09 | 2022-11-09 | Tangential surrounding type space array and system for deep craniocerebral noninvasive focusing stimulation |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202211400947.2A CN115887932B (en) | 2022-11-09 | 2022-11-09 | Tangential surrounding type space array and system for deep craniocerebral noninvasive focusing stimulation |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CN115887932A CN115887932A (en) | 2023-04-04 |
| CN115887932B true CN115887932B (en) | 2023-08-29 |
Family
ID=86479715
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN202211400947.2A Active CN115887932B (en) | 2022-11-09 | 2022-11-09 | Tangential surrounding type space array and system for deep craniocerebral noninvasive focusing stimulation |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN115887932B (en) |
Families Citing this family (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN117339111A (en) * | 2023-12-05 | 2024-01-05 | 首都医科大学宣武医院 | Be used for deep transcranial magnetic stimulation regulation and control treatment device |
| CN117482400B (en) * | 2023-12-27 | 2024-03-12 | 成都理工大学 | Time domain interferometry feature stimulation array and system for craniocerebral depth focus stimulation |
Citations (7)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CA2443819A1 (en) * | 2001-05-04 | 2002-11-14 | Board Of Regents, The University Of Texas System | Apparatus and methods for delivery of transcranial magnetic stimulation |
| CN105597234A (en) * | 2015-07-09 | 2016-05-25 | 北京大学 | Multilayer eccentric 8-shaped coil for deep site transcranial magnetic stimulation |
| CN110975152A (en) * | 2019-12-17 | 2020-04-10 | 华中科技大学 | Magnetic stimulation device and method capable of continuously working |
| CN113440731A (en) * | 2021-08-11 | 2021-09-28 | 成都理工大学 | Asymmetric special-shaped coil for craniocerebral electromagnetic stimulation and craniocerebral electromagnetic stimulation system |
| US11147982B1 (en) * | 2021-05-05 | 2021-10-19 | Kambix Innovations, Llc | Method and system for thermal stimulation of targeted neural circuits for neurodegenerative disorders |
| CN114129901A (en) * | 2021-12-20 | 2022-03-04 | 成都理工大学 | Follow-up type deep focusing electromagnetic stimulation system and stimulation method thereof |
| CN114191720A (en) * | 2021-12-20 | 2022-03-18 | 天津工业大学 | Cross coil for deep transcranial magnetic stimulation |
Family Cites Families (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| WO2018106843A1 (en) * | 2016-12-06 | 2018-06-14 | The Regents Of The University Of California | Optimal multi-electrode transcutaneous stimulation with high focality and intensity |
-
2022
- 2022-11-09 CN CN202211400947.2A patent/CN115887932B/en active Active
Patent Citations (7)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CA2443819A1 (en) * | 2001-05-04 | 2002-11-14 | Board Of Regents, The University Of Texas System | Apparatus and methods for delivery of transcranial magnetic stimulation |
| CN105597234A (en) * | 2015-07-09 | 2016-05-25 | 北京大学 | Multilayer eccentric 8-shaped coil for deep site transcranial magnetic stimulation |
| CN110975152A (en) * | 2019-12-17 | 2020-04-10 | 华中科技大学 | Magnetic stimulation device and method capable of continuously working |
| US11147982B1 (en) * | 2021-05-05 | 2021-10-19 | Kambix Innovations, Llc | Method and system for thermal stimulation of targeted neural circuits for neurodegenerative disorders |
| CN113440731A (en) * | 2021-08-11 | 2021-09-28 | 成都理工大学 | Asymmetric special-shaped coil for craniocerebral electromagnetic stimulation and craniocerebral electromagnetic stimulation system |
| CN114129901A (en) * | 2021-12-20 | 2022-03-04 | 成都理工大学 | Follow-up type deep focusing electromagnetic stimulation system and stimulation method thereof |
| CN114191720A (en) * | 2021-12-20 | 2022-03-18 | 天津工业大学 | Cross coil for deep transcranial magnetic stimulation |
Also Published As
| Publication number | Publication date |
|---|---|
| CN115887932A (en) | 2023-04-04 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| CN115887932B (en) | Tangential surrounding type space array and system for deep craniocerebral noninvasive focusing stimulation | |
| Wagner et al. | Three-dimensional head model simulation of transcranial magnetic stimulation | |
| Manola et al. | Modelling motor cortex stimulation for chronic pain control: electrical potential field, activating functions and responses of simple nerve fibre models | |
| Ren et al. | A novel electric design for electromagnetic stimulation-the slinky coil | |
| Jirsa et al. | Spatiotemporal forward solution of the EEG and MEG using network modeling | |
| Antonietti et al. | Spiking neural network with distributed plasticity reproduces cerebellar learning in eye blink conditioning paradigms | |
| Hsu et al. | A 3-D differential coil design for localized magnetic stimulation | |
| Wang et al. | Coupling magnetically induced electric fields to neurons: longitudinal and transverse activation | |
| CN106345056B (en) | Deep brain stimulation electrod-array optimization system based on machine learning | |
| Hsu et al. | Analysis of efficiency of magnetic stimulation | |
| Gomez et al. | Numerical analysis and design of single-source multicoil TMS for deep and focused brain stimulation | |
| Tarotin et al. | Model of impedance changes in unmyelinated nerve fibers | |
| Hsu et al. | Prediction of neural excitation during magnetic stimulation using passive cable models | |
| Davids et al. | A Huygens’ surface approach to rapid characterization of peripheral nerve stimulation | |
| CN113303815B (en) | Optimization method and system for multi-lead transcranial time interference electrical stimulation current parameters | |
| Cretu et al. | Magnetic coil design for evaluating the response of the spinal cord during magnetic stimulation | |
| Marinova et al. | A neural network inversion approach to electromagnetic device design | |
| Pourtaheri et al. | Thresholds for transverse stimulation: fiber bundles in a uniform field | |
| Chung et al. | Morphological Influence and Electric Field Direction’s Influence on Activation of Cortical Neurons in Electrical Brain Stimulation: A Computational Study | |
| Fang et al. | Design and Optimization of a Novel Multi-Quadrant Spatial Array for Non-Invasive Focalized Magnetic Stimulation of the Deep Brain | |
| Fang et al. | Optimum Design of the Eccentric Trapezoidal Magnetic Stimulation Coil Considering Stimulation Effect and Heat Dissipation | |
| Song et al. | Optimal Design of Transcupoint Magnetic Stimulation Coil with Trade-Off Between Stimulation Effect and Joule Heat Energy | |
| Reilly | Nerve stimulation of cows and other farm animals by time-varying magnetic fields | |
| Wartrnan et al. | High Resolution Computational Modeling of Transcranial Stimulation using the MIDA Head Model | |
| Aberra | Multi-Scale Modeling for Analysis and Design of Transcranial Electric and Magnetic Brain Stimulation |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| PB01 | Publication | ||
| PB01 | Publication | ||
| SE01 | Entry into force of request for substantive examination | ||
| SE01 | Entry into force of request for substantive examination | ||
| GR01 | Patent grant | ||
| GR01 | Patent grant |