CN115887932A - Tangential surrounding type spatial array and system for craniocerebral deep noninvasive focusing stimulation - Google Patents
Tangential surrounding type spatial array and system for craniocerebral deep noninvasive focusing stimulation Download PDFInfo
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Abstract
The invention discloses a tangential surrounding type spatial array and system for deep non-invasive focusing stimulation of cranium and brain, and relates to the technical field of cranium and brain electromagnetic stimulation. The spatial array comprises a plurality of tangential coils which are transversely arranged around the head of the human body and have the same geometric parameters; when the space array works, a plurality of stimulating currents in one-to-one correspondence are input into the plurality of tangential coils, the plurality of stimulating currents are used for generating a plurality of first induction electric field vectors which have the characteristics of similar amplitudes and small included angles at the deep part of the cranium through the plurality of tangential coils which flow through, and generating a plurality of second induction electric field vectors which have the characteristics of large amplitude difference and large included angles 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 favorably enhanced, the stimulating depth is effectively improved, and the purposes of space selective stimulation and stimulating focusing improvement are achieved. 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 brain electromagnetic stimulation, and particularly relates to a tangential surrounding type spatial array and system for non-invasive focusing stimulation of the deep part of the brain.
Background
Under the severe background that the incidence rate of global mental diseases is rising year by year and the base of patients is becoming huge, the mental diseases form a serious threat to the physical and mental health of people and the development of social economy. As a leading-edge nerve regulation and control means, the transcranial magnetic stimulation technology is called one of the four-brain science and technology in the 21 st century, has the characteristics of no wound, no pain and no need of 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 a 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 carried out, parameters of a stimulation system are set according to different stimulation purposes, and a stimulation pulse sequence with a specific time sequence is generated. During stimulation, a stimulation coil is placed over the target area of the head, and a time-varying pulsed stimulation current is then passed through the stimulation coil to cause an alternating induced magnetic field to be generated in the space surrounding the stimulation coil. Because the electrical conductivity and the magnetic conductivity of the biological tissue are not zero, the 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 to play a role in regulating nerves. In order to effectively regulate and control the target nerve tissue and reduce the influence on non-target neurons so as to reduce stimulation side effects, stimulation focality must be ensured.
Because the target area of mental diseases is usually positioned at a specific depth in the cranium, biological tissues in the cranium are complex, and the electric conductivity and the magnetic conductivity of different biological tissues are lower and unequal, the induced electric field generated in the stimulation process is quickly attenuated when longitudinally propagating in the cranium, and the effective induced electric field is difficult to reach the deep cranium. On the other hand, with the increase of stimulation depth, the divergence of an induction electric field generated by the traditional stimulation coil is serious, so that the strong stimulation coverage of half brain or whole brain is often caused, the stimulation depth and the stimulation focusing property cannot be considered, and the requirement of deep brain stimulation cannot be met. For example, the splayed coil is the most common commercial transcranial magnetic stimulation coil on the market at present, and the coil can generate an eddy current-shaped focusing stimulation area 1.5cm to 2cm below the scalp to realize cortical excitability regulation, but the target area of deep craniocerebral stimulation is usually located at a depth of more than 4cm below the scalp and exceeds the effective stimulation range of the splayed coil.
In order to further increase the stimulation depth of transcranial magnetic stimulation, researchers have proposed various deep brain stimulation coil structures such as a biconical stimulation coil, an H-coil and a concentric coil to improve the stimulation depth, but the structures all sacrifice the stimulation focusing property, expose a large area of non-target area tissues to stronger stimulation, and increase the risk of inducing stimulation side effects. 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 derivation, and multiple characteristic indexes for evaluating the deep brain stimulation effect are mutually restricted, and multi-objective optimization of the brain stimulation coil is difficult to achieve.
In conclusion, the deep stimulation effect of the biological craniocerebra is improved through the optimal design of the stimulation coil, and the realization of focused stimulation on the premise of ensuring the stimulation depth has important significance on the clinical treatment and scientific research of mental diseases.
Disclosure of Invention
The invention aims to provide a tangential surrounding type spatial array and a system for non-invasive focusing stimulation in the deep part of the cranium and aims to solve the problem that the existing cranium and brain electromagnetic stimulation technology cannot give consideration to both the stimulation depth and the stimulation focusing property.
In order to achieve the purpose, the invention adopts the following technical scheme:
in a first aspect, a tangential wraparound spatial array for deep craniocerebral noninvasive focused stimulation is provided, which comprises a plurality of tangential coils with the same geometric parameters and arranged transversely around a human head, wherein the tangential coils refer to coil structures which can be tangent 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 plurality of tangential coils are input into the plurality of tangential coils, wherein the plurality of stimulating currents are used for generating a plurality of first induced electric field vectors which have the characteristics of similar amplitudes and small included angles at the deep part of the cranium through the plurality of tangential coils which flow through the plurality of tangential coils, and generating a plurality of second induced electric field vectors which have the characteristics of large amplitude difference and large included angles at the superficial layer of the scalp.
Based on the above invention, a coil space array design scheme for non-invasive focusing stimulation in deep craniocerebral is provided, that is, the design scheme includes 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 refer to coil structures which can be tangent to the surface of the scalp of the head of the human body; when the coil space array works, a plurality of stimulating currents which are in one-to-one correspondence with the plurality of tangential coils are input into the plurality of tangential coils, wherein the plurality of stimulating currents are used for generating a plurality of first induced electric field vectors which have the characteristics of similar amplitudes and smaller included angles at the deep part of the cranium through the plurality of tangential coils which flow through the plurality of tangential coils, and generating a plurality of second induced electric field vectors which have the characteristics of larger amplitude difference and larger included angles at the shallow layer of the scalp, so that the superposition effect of the induced electric field at the deep part of the cranium can be enhanced, the stimulating depth can be effectively improved, the purposes of space selective stimulation and stimulating focusing property improvement can be realized, the biological tissues at the deep part of the subcutaneous part of the stimulating head, which is larger than 4cm, can be facilitated, and the requirement of the cranium stimulation on the stimulating depth can be met.
In one possible design, the current magnitudes of the plurality of stimulation currents are determined according to the following steps:
determining a multidimensional decision variable I = { B = { 1 ,B 2 ,…,B m ,…,B M And establishing a three-dimensional finite element numerical model of the tangential surrounding type space array and the human head, wherein M represents the total current of the stimulation currents, M represents a positive integer less than or equal to M, and B m A current magnitude variable representing the mth stimulation current in the plurality of stimulation currents, and a constraint condition of 1kA ≦ B m ≤5kA；
For the multi-dimensional decision change under the constraint conditionThe amount I is given an Initial value for a plurality of times, and a current magnitude Initial value group Initial _ I = { I } constituting the plurality of stimulation currents 1 ,I 2 ,…,I n ,…,I N Wherein N represents the total number of times of assigning the initial value, N represents a positive integer of N or less, and I n A set of initial current level values representing the plurality of stimulation currents resulting from the nth assignment of initial values;
importing the Initial current magnitude value group Initial _ I into the three-dimensional finite element numerical model for simulation operation, and acquiring N groups of craniocerebral deep stimulation characteristic index data which correspond to N groups of Initial current magnitude values in the Initial current magnitude value group Initial _ I in a one-to-one manner, wherein each group of craniocerebral deep stimulation characteristic index data in the N groups of craniocerebral deep stimulation characteristic index data comprises a simulation operation result numerical value of at least one craniocerebral deep stimulation characteristic index;
taking the N groups of initial values of the current as input items, taking the N groups of data of the brain deep stimulation characteristic indexes as output items, and carrying out rating verification modeling on an artificial intelligence model based on a support vector machine, a K nearest neighbor method, a random gradient descent method, multivariate linear regression, a multilayer perceptron, a decision tree, a back propagation neural network or a radial basis function network to obtain a prediction model of each brain deep stimulation characteristic index in the at least one brain deep stimulation characteristic index and based on the multi-dimensional decision variable I;
taking the prediction model of each brain deep stimulation characteristic index based on the multi-dimensional decision variable I as an optimization objective function, and performing multi-objective optimization by adopting an NSGA-II algorithm under the constraint condition to obtain the optimal solution of the multi-dimensional decision variable I;
and taking the optimal solution of the multi-dimensional decision variable I as the current magnitude of the plurality of stimulation currents.
In one possible design, the multidimensional decision variable I is given an Initial value a plurality of times under the constraint condition, and a current magnitude Initial value set Initial _ I = { I = } of the plurality of stimulation currents is formed 1 ,I 2 ,…,I n ,…,I N And (4) the method comprises the following steps:
at the above-mentioned rangeSampling the multidimensional decision variable I for multiple times by adopting a Latin hypercube function under the beam condition to assign Initial values, and forming a current magnitude Initial value group Initial _ I = { I } of the multiple stimulation currents 1 ,I 2 ,…,I n ,…,I N Wherein N represents the total number of times of assigning the initial value, N represents a positive integer of N or less, and I n A set of initial current level values representing the plurality of stimulation currents obtained by assigning the initial values for the nth time.
In one possible design, the at least one index of stimulation characteristics for deep craniocerebral stimulation includes any one or any combination of a stimulation intensity, a focal area and a longitudinal decay rate, wherein the stimulation intensity refers to a positive-direction index represented by a maximum value of an induced electric field of an intracranial target area on an X test line and a Y test line, the focal area refers to a negative-direction index represented by an area of a region formed by data points on an intracranial test plane where the stimulation intensity is greater than a stimulation threshold, the longitudinal decay rate refers to another positive-direction index represented by a ratio of an amplitude of the induced electric field at the deep craniocerebral test target point on the Z test line to an amplitude of the induced electric field at a superficial 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 an origin, an X axis in the XYZ coordinate system is XYZ of the human head, a Y axis in the right of the intracranial test line is a front direction of the human head, a Y axis in the intracranial test line = a positive direction of the scalp, and the X test line is represented by 0-L, and the X test line is represented by 0-X test line and the positive direction is represented by a positive direction of the X test line.
In one possible design, under the constraint condition, performing multi-objective optimization by using an NSGA-II algorithm to obtain an optimal solution of the multi-dimensional decision variable I, including:
performing multi-objective optimization by adopting an NSGA-II algorithm 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 so, acquiring the optimal solution of the multi-dimensional decision variable I according to the current multi-objective optimization result, otherwise, self-adding 1 to the current evolutionary algebra, and then returning to the step of rating, verifying and modeling.
In one possible embodiment, the tangential coil is composed of at least two longitudinally arranged coil elements.
In a possible design, the tangential coil adopts the type B coil including current input terminal, vertical lower part coil unit, vertical long side conductor, vertical upper portion coil unit and current output terminal, wherein, vertical lower part coil unit adopts the fan-shaped structure of making through the from inside to outside coiling mode, vertical upper portion coil unit adopts the fan-shaped structure of making through the outside-in coiling mode, current input terminal vertical lower part coil unit vertical long side conductor vertical upper portion coil unit with current output terminal electricity in proper order connects, vertical lower part coil unit with vertical upper portion coil unit has the space contained angle, makes vertical lower part coil unit with vertical upper portion coil unit can respectively with the scalp surface of human head is tangent.
In one possible design, the plurality of tangential coils comprises at least two pairs of the B-shaped coils, wherein each pair of the B-shaped coils adopts an arrangement mode that long sides are close and back to back when being transversely arranged around the head of the human body.
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 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 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 correspond one-to-one to a plurality of tangential coils in a tangential wraparound spatial array as described in the first aspect or any possible design of the first aspect and used for deep craniocerebral noninvasive focused stimulation, wherein each of the plurality of stimulation modules contains the corresponding tangential coil.
In a possible design, the stimulation module further includes 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 to 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 to a low potential end of the energy storage capacitor through the current detection unit, so as 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 the voltage amplitude 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 a 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 stimulating current loop according to a second driving signal after receiving the second driving signal from the control module;
and 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 adjusting signal after receiving the current adjusting signal which is from the control module and is obtained based on the two paths of input signals.
The beneficial effect of above-mentioned scheme:
(1) The invention provides a design scheme of a coil space array for deep non-invasive focusing stimulation of cranium and brain, which comprises a plurality of tangential coils which are transversely arranged around the head of a human body and have the same geometric parameters, wherein the tangential coils refer to coil structures which can be tangent to the surface of the scalp of the head of the human body; when the coil space array works, a plurality of stimulating currents which are in one-to-one correspondence with the plurality of tangential coils are input into the plurality of tangential coils, wherein the plurality of stimulating currents are used for generating a plurality of first induced electric field vectors which have the characteristics of similar amplitudes and smaller included angles at the deep part of the cranium and generating a plurality of second induced electric field vectors which have the characteristics of larger amplitude difference and larger included angles at the shallow layer of the scalp through the plurality of tangential coils which flow through the plurality of tangential coils, so that the superposition effect of the induced electric fields in the deep part of the cranium can be enhanced, the stimulating depth can be effectively improved, the purposes of space selective stimulation and stimulating focusing can be realized, the biological tissues at the depth of more than 4cm below the subcutaneous part of the stimulating head can be facilitated, and the requirement of the cranium stimulation on the stimulating depth can be met;
(2) The configuration scheme of the in-array stimulation current parameters based on the NSGA-II algorithm is further provided, the optimal in-array stimulation current parameters can be obtained, the purpose of global optimization of a space array is achieved, and the problem that the optimization difficulty of the stimulation array is large because the dominant analytic relation between the stimulation current parameters and the deep brain stimulation characteristics cannot be directly obtained through mathematical derivation at present is solved;
(3) The device can noninvasively generate an obvious focusing stimulation area in the deep part of the cranium, and compared with the traditional splayed coil array, the device can improve the stimulation intensity by 4.79 times, reduce the focusing area by 78.5 percent and improve the longitudinal attenuation rate by 3.76 times, so that the improvement of the stimulation depth and the focusing property can be considered, and the focusing stimulation effect in the deep part of the cranium can be obviously enhanced;
(4) Can keep the advantages of non-invasive biological magnetic stimulation and no need of operation, does not need to physically move the stimulating coil in the stimulating process, is friendly to clinical operation and has low economic cost.
Drawings
In order to more clearly illustrate the embodiments of the present invention or the technical solutions in the prior art, the drawings used in the description of the embodiments or the prior art will be briefly described below, it is obvious that the drawings in the following description are only some embodiments of the present invention, and for those skilled in the art, other drawings can be obtained according to the drawings without creative efforts.
Fig. 1 is a schematic diagram of an arrangement relationship between a tangential surrounding spatial array and a human head provided in an embodiment of the present application, where fig. 1 (a) shows a schematic diagram of a three-dimensional structure of the arrangement relationship, fig. 1 (b) shows a schematic diagram of a top-view structure of the arrangement relationship, fig. 1 (c) shows a schematic diagram of a side-view structure of the arrangement relationship, and fig. 1 (d) shows a schematic diagram of a front-view structure of the arrangement relationship.
Fig. 2 is a schematic winding structure diagram of 8B-type coils provided in the embodiment of the present application.
Fig. 3 is a schematic diagram of a current magnitude determination process of a plurality of stimulation currents according to an embodiment of the present application.
Fig. 4 is a schematic diagram of a spatial position relationship between an XYZ test line, an intracranial test plane, and a scalp vertex provided in the embodiment of the present application.
Fig. 5 is a diagram illustrating an artificial intelligence model structure based on a back propagation neural network and an example of a prediction effect of 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 focal area index, and fig. 5 (d) shows an example of a prediction effect of a prediction model for a longitudinal attenuation rate index.
FIG. 6 is an exemplary diagram of an induced electric field distribution generated by a tangential surround type spatial array in a deep part of a brain according to an embodiment of the present application.
Fig. 7 is an exemplary diagram of an induced electric field distribution generated in the deep part of the cranium by a conventional splayed coil array provided by an embodiment of the present application.
Fig. 8 is a schematic structural diagram of a transcranial magnetic stimulation system provided by an embodiment of the 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 invention or the technical solutions in the prior art, the present invention will be briefly described below with reference to the accompanying drawings and the embodiments or the description of the prior art, it is obvious that the following description of the structure of the drawings is only some embodiments of the present invention, and it is also possible for those skilled in the art to obtain other drawings based on the drawings without creative efforts. It should be noted that the description of the embodiments is provided to help understanding of the present invention, and the present invention is not limited thereto.
It will be understood that, although the terms first, 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 present invention.
It should be understood that, for the term "and/or" as may appear herein, it is merely an associative relationship that describes an associated object, meaning that three relationships may exist, e.g., a and/or B may mean: a exists alone, B exists alone or A and B exist at the same time; as another example, A, B and/or C, may indicate the presence of any one or any combination of A, B and C; for the term "/and" as may appear herein, which describes another associative object relationship, it means that two relationships may exist, e.g., a/and B, may mean: a exists singly or A and B exist simultaneously; in addition, with respect to the character "/" which may appear herein, it generally means that the former and latter associated objects are in an "or" relationship.
Example (b):
as shown in fig. 1, the tangential surrounding type spatial array for deep craniocerebral non-invasive focused stimulation provided by the first aspect of the present embodiment includes, but is not limited to, a plurality of tangential coils having the same geometric parameters and arranged transversely around the head of a human body, wherein the tangential coils refer to a coil structure capable of being tangent to the surface of the scalp 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 plurality of tangential coils are input into the plurality of tangential coils, wherein the plurality of stimulating currents are used for generating a plurality of first induced electric field vectors which have the characteristics of similar amplitudes and small included angles at the deep part of the cranium through the plurality of tangential coils which flow through the plurality of tangential coils, and generating a plurality of second induced electric field vectors which have the characteristics of large amplitude difference and large included angles at the superficial layer of the scalp.
In the specific structure of the tangential wraparound spatial array, as shown in fig. 1, each of the plurality of tangential coils is used to introduce a corresponding stimulation current so as to generate a corresponding induced electric field vector. Because the tangential coil can be tangent to the surface of the scalp of the human head, the intracranial non-longitudinal induced electric field component accumulation can be reduced, and the focusing property of deep brain stimulation is improved. Because the plurality of tangent coils are transversely arranged around the head of the human body, the centers of the coils and the center of the deep part of the brain can be basically positioned at the same height, the electromagnetic energy can be further favorably dragged to the deep part of the brain, and the deep brain stimulation effect is improved. Meanwhile, when the tangential surrounding type space array works, the plurality of stimulating currents can be input into the plurality of tangential coils, the plurality of first induced electric field vectors which are generated in the deep part of the cranium and have the characteristics of similar amplitudes and small included angles can be utilized, so that the longitudinal induced electric field synthesized in the deep part of the cranium is large, the purpose of enhancing the deep part of the cranium is realized, and the plurality of second induced electric field vectors which are generated in the shallow layer of the scalp and have the characteristics of large amplitude difference and large included angles can be utilized, so that the longitudinal induced electric field synthesized in the shallow layer of the scalp is small, and the purpose of weakening the shallow layer induced electric field is realized. Therefore, through the structural design of the tangential surrounding type space array and the input of the plurality of stimulating currents, the superposition effect of an induction electric field in a deep area of the cranium can be favorably enhanced, the stimulating depth is effectively improved, the purposes of spatially selective stimulation and stimulating focusing are realized, the biological tissues in the position of the subcutaneous part of the stimulating head, which is more than 4cm in depth, can be favorably stimulated, and the requirement of the cranium on the stimulating depth is met.
Preferably, the tangential coil comprises at least two longitudinal arrangement's coil unit to promote geometric flexibility, even the coil unit can constitute multiple space contained angle about the upper and lower, more laminate human scalp structure, reduce the interior electromagnetic energy loss of space, further help improving the amazing focus nature. 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, where 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, 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 spatial included angle, so that the longitudinal lower coil unit 14 and the longitudinal upper coil unit 16 can be respectively tangent to the surface of the scalp of the human head. As shown in fig. 1, the upper and lower portions of the two B-type coils (1,8) on the left side and the right side of the forehead form an included angle 9; the upper and lower parts of two B-shaped coils (2,3) positioned in front of 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 occipital part and the right side of the rear occipital part form an included angle 11; the upper and lower parts of the two B-shaped coils (6,7) positioned behind and in front of the left ear form an included angle 12, so that the structure is more in line with the ergonomics. In addition, as shown in fig. 2, the reference numbers of the components in the B-type coils 2 to 8 can be derived according to the reference numbers of the components in the B-type coil 1, and are not described herein again.
Preferably, the plurality of tangential coils comprise at least two pairs of B-shaped coils, wherein each pair of B-shaped coils adopt an arrangement mode that long sides are close together and back to back when being transversely arranged around the head of the human body. As shown in fig. 1 and 2, two B-type coils (1,8) positioned on the left side of the forehead and the right side of the forehead are respectively tangent to the scalp in the longitudinal direction, and two longitudinal long-side conductors (15, 20) are close to each other and are placed in a back-to-back state at the forehead of the head, so that forehead stimulation is formed. As shown in fig. 2, since the stimulating current directions of all the B-type coils are the same, all the B-type coils are from bottom to top, the induced electric fields generated by the coils under the long-side conductors are in the same direction (taking the B-type coil on the left side of the forehead as an example, the stimulating current flowing through the B-type coil is in the counterclockwise direction, the induced magnetic field below the coil is strengthened, and the induced magnetic field in the direction is weakened according to the lenz theorem, so that the induced electric field in the clockwise direction is induced, and similarly, the stimulating current flowing through the B-type coil on the right side of the forehead is in the clockwise direction, so that the induced electric field is in the counterclockwise direction, and thus when the two B-type coils are placed back to back, the induced electric fields are in the tangential positions between the two B-type coils, and the induced electric fields are in the same direction), the intracranial longitudinal induced electric fields can be effectively superposed, the stimulating strength can be improved, and finally, an obvious target area can be formed under the center of the B-type coils. In addition, for example, as shown in fig. 1, the plurality of tangential coils include four pairs of the B-type coils that are uniformly distributed in four directions of front, rear, left, and right with the center of the head as the origin, that is, two B-type coils (1,8) located on the left side of the forehead and on the right side of the forehead, two B-type coils (2,3) 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 occipital section and on the right side of the occipital section, and two B-type coils (6,7) located behind the left ear and in front of the left ear.
Considering that after the geometric structure of the tangential surrounding spatial array and the position relative to the head of the human body are determined, the deep brain stimulation effect is further determined by the configuration result of the stimulation current parameters in the array (i.e., the current magnitudes of the multiple stimulation currents), but the explicit analytical relationship between the stimulation current parameters in the array and the deep brain stimulation characteristics cannot be directly obtained through mathematical derivation, which results in a high optimization difficulty of the stimulation array (i.e., the explicit analytical relationship between the stimulation current parameters and the deep brain stimulation characteristics cannot be obtained through mathematical derivation due to the complexity of the bio-electromagnetic stimulation model, and there are constraints among multiple characteristic indicators for evaluating the deep brain stimulation effect, which results in a high multi-objective optimization difficulty of the stimulation coils and thus a high optimization difficulty of the array), in order to solve this problem, the present embodiment further provides an intra-array stimulation current parameter configuration scheme based on the NSGA-II algorithm to obtain the optimal intra-array stimulation current parameters, so as to realize global optimization of the spatial array, that the current magnitudes of the multiple stimulation currents may be determined according to, but not limited to the following steps S1 to S6, as shown in fig. 3.
S1, determining a multidimensional decision variable I = { B = 1 ,B 2 ,…,B m ,…,B M And establishing a three-dimensional finite element numerical model of the tangential surrounding type space array and the human head, wherein M represents the total current of the stimulation currents, M represents a positive integer less than or equal to M, and B m A current magnitude variable representing the mth stimulation current in the plurality of stimulation currents, and a constraint condition of 1kA ≦ B m ≤5kA。
In the step S1, the multidimensional decision variable I may be determined by analyzing the geometric structure of the tangentially-wound spatial array and checking the total number of directional coils in the array. The three-dimensional finite element numerical model is a three-dimensional finite element model, can be obtained by conventional establishment by using the existing finite element analysis method, and needs to be converted into a three-dimensional finite element numerical model for facilitating subsequent simulation operation application in Matlab software
A script file that can be recognized by Matlab software. Further, kA represents the current magnitude unit and is kilo amperes.
S2, giving Initial values to the multidimensional decision variable I for multiple times under the constraint condition to form an Initial current value set Initial _ I = { I ] of the multiple stimulation currents 1 ,I 2 ,…,I n ,…,I N Wherein N represents the total number of initial value assignments, N represents a positive integer less than or equal to N, and I n Indicates the order of n-th assignmentAnd the initial value of a group of current magnitudes of the plurality of stimulation currents is obtained.
In step S2, specifically, the multidimensional decision variable I is sampled by a latin hypercube function under the constraint condition to obtain Initial values, and a current magnitude Initial value group initiai _ I = { I } of the plurality of stimulation currents is formed 1 ,I 2 ,…,I n ,…,I N Wherein N represents the total number of initial value assignments, N represents a positive integer less than or equal to N, and I n A set of initial values of current magnitudes representing the plurality of stimulation currents obtained by assigning initial values for the nth time. The Latin hypercube function is an existing function, and the specific mode of sampling and assigning initial values by using the Latin hypercube function is an existing conventional mode.
And S3, importing the Initial current magnitude value group Initial _ I into the three-dimensional finite element numerical model for simulation operation, and acquiring N groups of craniocerebral deep stimulation characteristic index data which correspond to N groups of Initial current magnitude values in the Initial current magnitude value group Initial _ I one by one, wherein each group of craniocerebral deep stimulation characteristic index data in the N groups of craniocerebral deep stimulation characteristic index data comprises a simulation operation result numerical value of at least one craniocerebral deep stimulation characteristic index.
In step S3, the at least one index of deep brain stimulation characteristics is used to analyze the three-dimensional spatial distribution characteristics of the intracranial induction electric field, so as to verify the deep brain stimulation effect of the tangential surrounding spatial array. Specifically, the at least one index of the brain deep stimulation characteristics includes, but is not limited to, any one of or any combination of stimulation intensity, focal area and longitudinal attenuation rate, wherein the stimulation intensity refers to a positive index represented by a maximum value of an induced electric field of an intracranial target area on an X test line and a Y test line, the focal area refers to a negative index represented by an area of a region formed by data points on an intracranial test plane where the stimulation intensity is greater than a stimulation threshold, the longitudinal attenuation rate refers to another positive index represented by a ratio of an amplitude of an induced electric field at a brain deep test target point on a Z test line to an amplitude of an induced electric field at a scalp shallow 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 having a scalp vertex as an origin of coordinates, a positive X-axis direction in the XYZ coordinate system is a right side of the human head, a positive Y-axis direction in the XYZ coordinate system is a front side of the human head, a positive Z-axis direction in the XYZ coordinate system is an upper side of the human head, the X test line is represented by Y =0 and Z = -L, the Y test line is represented by X =0 and Z = -L, the Z test line is represented by X =0 and Y =0, the intracranial test plane is represented by X =0, and L represents a target depth from the scalp vertex. 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. In addition, the simulation operation may be specifically performed in Matlab software.
And S4, taking the N groups of initial values of the current as input items, taking the N groups of data of the brain deep stimulation characteristic indexes as output items, and carrying out rating verification modeling on an artificial intelligence model based on a support vector machine, a K nearest neighbor method, a random gradient descent method, multivariate linear regression, a multilayer perceptron, a decision tree, a back propagation neural network or a radial basis function network and the like to obtain a prediction model of each brain deep stimulation characteristic index in the at least one brain deep stimulation characteristic index and based on the multi-dimensional decision variable I.
In the step S4, the support vector machine, the K nearest neighbor method, the stochastic 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 existing artificial intelligence methods; taking a Back Propagation (BP) neural network as an example, the BP neural network is a multilayer feedforward neural network (namely, the BP neural network consists of 3 parts, namely an input layer, a hidden layer, an output layer and the like) which realizes a BP neural network algorithm (namely, an intelligent algorithm formed by simulating the biological tissue form of a human brain) and is trained according to an error Back Propagation algorithm, and the basic idea is a gradient descent method, and repeated learning training is carried out by utilizing error Back Propagation to enable the actual output value of the network to beThe error from the expected output value is minimum), has the advantages of simple model, low computation and the like, can fit the internal relation between the decision variable and the target function by learning various training sets to solve the problem of limited fitting capability of the dominant function, and is the most widely applied neural network model. The specific process of the calibration verification modeling comprises a calibration process and a checking process of the model, namely, a process of matching the simulation result with the actual measurement data by comparing the simulation result of the model with the actual measurement data and then adjusting the parameters of the model according to the comparison result, so that the prediction model of each brain deep stimulation characteristic index based on the multi-dimensional decision variable I can be obtained by a conventional calibration verification modeling mode. For example, with the artificial intelligence model based on the back propagation neural network as shown in fig. 5 (a), it is assumed that there are M input nodes in the input layer to correspond to the multidimensional decision variable I one by one, and there are 3 output nodes in the output layer to correspond to the stimulus intensity, the focus area, and the longitudinal decay rate one by one, and it is also assumed that there are training times net.trainparam.epochs =1000, learning rates net.trainparam.lr =0.01, training minimum errors net.trainparam.goal =0.000001, and taking the number of groups N =50, training data groups number TrainN, and test data groups number TestN, which satisfy: trainN + TestN = N =50; a prediction model E of the stimulus intensity and based on the multi-dimensional decision variable I when the number of test data sets TestN =5 BP (I) The comparison result between the predicted data and the actual data of (2) can be as shown in fig. 5 (b): correlation coefficient R between two data 2 About 0.98; a prediction model S of the area of focus and based on the multi-dimensional decision variable I when the number of test data sets 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 prediction model δ of the longitudinal decay rate and based on the multi-dimensional decision variable I when the number of test data sets TestN =5 BP (I) The comparison between the predicted data and the actual data of (c) can be as shown in fig. 5 (d): correlation coefficient R between two data 2 About 0.95; this may indicate that the reverse transmission is based onThe artificial intelligent model of the broadcast neural network carries out calibration verification modeling, and three prediction models E with higher reliability can be obtained BP (I)、 S 70,BP (I) And delta BP (I)。
And S5, taking the prediction model of each brain deep stimulation characteristic index based on the multi-dimensional decision variable I as an optimization objective function, and performing multi-objective optimization by adopting an NSGA-II algorithm under the constraint condition to obtain the optimal solution of the multi-dimensional decision variable I.
In step S5, since the stimulation intensity is a positive indicator, the corresponding optimization direction is the maximum value: max (E) BP (I) ); since the focusing area is a negative indicator, the corresponding optimization direction is the minimum value: min (S) 70,BP (I) ); since the longitudinal attenuation rate is another forward indicator, the corresponding optimization direction is also the maximum value: max (delta) BP (I) ). The NSGA-II (Non-dominated Sorting Genetic Algorithm-II, second generation of Non-dominated Sorting Genetic Algorithm) Algorithm is one of the most popular multi-target Genetic algorithms, and adopts a rapid Non-dominated Sorting Algorithm (namely, the general process is that a population is initialized, the population is subjected to Non-dominated Sorting, and a generation of offspring population is obtained through selection, crossing and variation of the Genetic Algorithm, at the moment, the evolution algebra is 1, the rapid Non-dominated Sorting is carried out from the evolution algebra being 2, the crowdedness of each Non-dominated layer individual is calculated to form a new parent population, a 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 the NSGA (Non-dominated Sorting Genetic Algorithm), the operation speed and robustness of the Algorithm are improved, the method is suitable for solving the multi-target optimization problem of the spatial array, and therefore, under the constraint condition, the multi-target optimization is carried out through adopting the NSGA-II Algorithm, and the multi-target decision-target optimization is obtained. Specifically, under the constraint condition, an NSGA-II algorithm is adopted to perform multi-objective optimization to obtain the optimal solution of the multi-dimensional decision variable I, including but not limited to the following: performing multi-objective optimization by adopting an NSGA-II algorithm under the constraint condition; determining a current in the NSGA-II algorithmWhether the evolution algebra exceeds a preset maximum allowable evolution algebra or not; if so, acquiring the optimal solution of the multi-dimensional decision variable I according to the current multi-objective optimization result, otherwise, self-adding 1 to the current evolutionary algebra, and then returning to the step of performing the calibration verification modeling (namely returning to execute the step S4).
And S6, taking the optimal solution of the multidimensional decision variable I as the current magnitude of the plurality of stimulation currents.
Therefore, based on the configuration scheme of the in-array stimulation current parameters described in the foregoing steps S1 to S6, the optimal in-array stimulation current parameters can be obtained, and the purpose of global optimization of the spatial array is achieved.
In this embodiment, based on the structural design of the tangential surrounding spatial array and the configuration scheme of the stimulation current parameters in the array, the following comparative tests (a) and (B) are also performed:
(A) The length of the long side of the B-type coil is 40mm, the wire diameter of the lead is 3mm × 4mm, and the total number of turns K =16, then the tangential surrounding type space array of the embodiment is constructed based on the B-type coil (namely, a plurality of tangential coils comprise four pairs of B-type coils which are uniformly distributed in four front, back, left and right directions with the head center as the origin), a scalp 57 and cerebral gray matter 58 are modeled to form a human head model, and the optimal stimulation current of the space array {2028A,2426A,4771A,4570A,1438A,3581A,1731A,2442A } is obtained by utilizing the intra-array stimulation current parameter configuration scheme. The distribution of the induced electric field generated by the tangentially-surrounding spatial array at the intracranial target plane is shown in FIG. 6 (the solid line with arrows in the figure represents the vector of the spatially-induced electric field). As can be seen from FIG. 6, the induced electric field generated by the tangential surround type spatial array can form a distinct focal region 59 in the deep part of the cranium; and obtaining that the stimulation intensity of the tangential surrounding type space array generated at the stimulation depth =10cm is 11.57V/m and the focusing area is 23.67cm through finite element numerical analysis 2 And a longitudinal decay rate of 2.43;
(B) Get single circular coil external diameter R 1 =35mm, wire diameter of 3mm × 4mm, total number of turns of 16, to form a conventional splayed coil array as a control array, and also for the scalp 57 and brainThe gray matter 58 is modeled to form a human head model. The joule loss of the conventional figure-eight coil array is equal to the joule loss of the tangentially-wound spatial array when the stimulation current in each single circular coil of the array is equal and is 3734A. At this time, the induced electric field distribution generated by the conventional splayed coil array on the intracranial target plane 56 is shown in fig. 7 (the solid line with an arrow in the figure represents a space induced electric field vector), and the focal region 60 of the generated induced electric field is close to the top of the scalp, is located in the shallow cortex (as indicated by the dashed box in the figure), and cannot reach the deep part of the cranium; and obtaining the stimulation intensity of the traditional splayed coil array at the stimulation depth =10cm and the focusing area of the traditional splayed coil array by finite element numerical analysis, wherein the stimulation intensity is 2V/m and the focusing area is 110cm 2 And a longitudinal decay rate of 0.51.
Based on the results of the above comparative tests (a) and (B), it can be seen that, compared with the conventional splayed coil array, the induced electric field distribution pattern generated by the tangential surround type spatial array provided in this embodiment at the deep part of the brain is more ideal, that is, at a stimulation depth of =10cm, the tangential surround type spatial array provided in this embodiment can generate an obvious focused stimulation region, and compared with the conventional splayed coil array, the stimulation intensity can be increased by 4.79 times, the focusing area can be reduced by 78.5%, and the longitudinal attenuation rate can be increased by 3.76 times, so that both the improvements of the stimulation depth and the focusing property can be achieved, and the focused stimulation effect at the deep part of the brain can be significantly enhanced.
As shown in fig. 8, the second aspect of the present embodiment provides a transcranial magnetic stimulation system applying the tangential surrounding type spatial array of the first aspect, including, but not limited to, a control module, a dc power module, a charging switch, and a storage stimulation circuit, wherein the storage 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 correspond one-to-one to a plurality of tangential coils in a tangential wraparound spatial array as described in the first aspect and used for deep craniocerebral noninvasive focused stimulation, wherein each of the plurality of stimulation modules contains a corresponding 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 be, but is not limited to, controlling on or off of the dc charging loop, which may be specifically implemented by a microcontroller of a model STM32F105 series. The dc power supply module is used for providing high-voltage dc power, and as shown in fig. 8, may specifically but not limited to include a power frequency power supply (which is used for providing 220V and 50Hz power frequency commercial power), a rectifier filter circuit, an inverter circuit, a boost circuit, a rectifier circuit, and the like, which are electrically connected in sequence. The charging switch can be realized by a conventional electric control switch. The plurality of stimulation modules are used for inputting the plurality of stimulation currents to the plurality of tangential directions so as to realize the transcranial magnetic stimulation effect of the tangential surrounding type space array; as shown in fig. 9, the stimulation module 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 to 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 to a low potential end of the energy storage capacitor through the current detection unit, so as to form a stimulation current loop; the voltage detection unit is connected in parallel at two ends of the energy storage capacitor and is used for monitoring voltage amplitudes at two ends of the energy storage capacitor and taking a detected voltage signal as one input signal of the control module; the current detection unit is used for taking a 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 a second driving signal after receiving the second driving signal from the control module; and 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 adjusting signal after receiving the current adjusting signal which is from the control module and is obtained 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.
For the working process, working details, and technical effects of the foregoing system provided in the second aspect of this embodiment, reference may be made to the tangential surrounding type spatial array described in the first aspect, which is not described herein again.
Finally, it should be noted that: the above description is only a preferred embodiment of the present invention, and is not intended to limit the scope of the present invention. Any modification, equivalent replacement, or improvement made within the spirit and principle of the present invention should be included in the protection scope of the present invention.
Claims (10)
1. A tangential surrounding type space array for the deep non-invasive focusing stimulation of the cranium and brain is characterized by comprising 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 coil structures which can be tangent to the surface of the scalp 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 plurality of tangential coils are input into the plurality of tangential coils, wherein the plurality of stimulating currents are used for generating a plurality of first induced electric field vectors which have the characteristics of similar amplitudes and small included angles at the deep part of the cranium through the plurality of tangential coils which flow through the plurality of tangential coils, and generating a plurality of second induced electric field vectors which have the characteristics of large amplitude difference and large included angles at the superficial layer of the scalp.
2. The tangential wraparound spatial array of claim 1, wherein the current magnitudes of the plurality of stimulation currents are determined by:
determining a multidimensional decision variable I = { B = { 1 ,B 2 ,…,B m ,…,B M And establishing a three-dimensional finite element numerical model of the tangential surrounding type space array and the human head, wherein M represents the total current of the stimulation currents, M represents a positive integer less than or equal to M, and B m A current magnitude variable representing the mth stimulation current in the plurality of stimulation currents, and a constraint condition of 1kA ≦ B m ≤5kA；
Giving Initial values to the multidimensional decision variable I for multiple times under the constraint condition to form an Initial current magnitude value set Initial _ I = { I ] of the multiple stimulation currents 1 ,I 2 ,…,I n ,…,I N Wherein N represents the total number of initial value assignments, N represents a positive integer less than or equal to N, and I n A set of initial current level values representing the plurality of stimulation currents resulting from the nth assignment of initial values;
introducing the Initial current magnitude value group Initial _ I into the three-dimensional finite element numerical model for simulation operation, and acquiring N groups of craniocerebral deep stimulation characteristic index data which are in one-to-one correspondence with N groups of Initial current magnitude values in the Initial current magnitude value group Initial _ I, wherein each group of craniocerebral deep stimulation characteristic index data in the N groups of craniocerebral deep stimulation characteristic index data comprises a simulation operation result numerical value of at least one craniocerebral deep stimulation characteristic index;
taking the N groups of initial values of the current as input items, taking the N groups of data of the brain deep stimulation characteristic indexes as output items, and carrying out rating verification modeling on an artificial intelligence model based on a support vector machine, a K nearest neighbor method, a random gradient descent method, a multivariate linear regression, a multilayer perceptron, a decision tree, a back propagation neural network or a radial basis function network to obtain a prediction model of each brain deep stimulation characteristic index in the at least one brain deep stimulation characteristic index and based on the multidimensional decision variable I;
taking the prediction model of each brain deep stimulation characteristic index based on the multi-dimensional decision variable I as an optimization objective function, and performing multi-objective optimization by adopting an NSGA-II algorithm under the constraint condition to obtain the optimal solution of the multi-dimensional decision variable I;
and taking the optimal solution of the multi-dimensional decision variable I as the current magnitude of the plurality of stimulation currents.
3. The tangential wraparound spatial array of claim 2, wherein an Initial value is assigned to the multi-dimensional decision variable I a plurality of times under the constraint condition, and an Initial value set of current magnitudes initiai _ I = { I } constituting the plurality of stimulation currents 1 ,I 2 ,…,I n ,…,I N And (4) the method comprises the following steps:
under the constraint condition, sampling the multidimensional decision variable I for multiple times by adopting a Latin hypercube function to assign Initial values, and forming a current magnitude Initial value group Initial _ I = { I } of the multiple stimulation currents 1 ,I 2 ,…,I n ,…,I N Wherein N represents the total number of initial value assignments, N represents a positive integer less than or equal to N, and I n A set of initial current level values representing the plurality of stimulation currents obtained by assigning the initial values for the nth time.
4. The tangential wraparound spatial array of claim 2, wherein the at least one index of craniocerebral deep stimulation characteristics includes any one or any combination of a stimulation intensity, a focal area, and a longitudinal attenuation rate, wherein the stimulation intensity is a positive-direction index represented by a maximum value of an intracranial target induced electric field on an X test line and a Y test line, the focal area is another positive-direction index represented by an area formed by data points on an intracranial test plane where the stimulation intensity is greater than a stimulation threshold, the longitudinal attenuation rate is another positive-direction index represented by 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 superficial 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 a coordinate system with a scalp vertex as an origin, the X-axis in the XYZ coordinate system is to the right of the head, the Y-axis in the coordinate system is 0 = positive-direction, and the X-axis in the X test line is 0-L =0, and the X-X test line is represented by 0-L, and the head is represented by 0-X test line.
5. The tangential wraparound spatial array of claim 2, 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:
performing multi-objective optimization by adopting an NSGA-II algorithm 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 so, acquiring the optimal solution of the multi-dimensional decision variable I according to the current multi-objective optimization result, otherwise, self-adding 1 to the current evolutionary algebra, and then returning to the step of rating verification modeling.
6. The tangential wraparound spatial array of claim 1, wherein the tangential coil is comprised of at least two longitudinally aligned coil elements.
7. The tangential surround type spatial array according to claim 1, wherein the tangential coil is 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) is a fan-shaped structure made by winding from inside to outside, the longitudinal upper coil unit (16) is a fan-shaped structure made by winding from outside to inside, 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 spatial angle, 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.
8. The tangentially-wound spatial array of claim 7, wherein said plurality of tangential coils comprises at least two pairs of said B-coils, wherein each pair of said B-coils are arranged in a back-to-back arrangement with their long sides close together when arranged transversely around the head of the human.
9. A 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 correspond one-to-one to a plurality of tangential coils in a tangential wraparound spatial array as claimed in any one of claims 1 to 8 and used for deep craniocerebral noninvasive focused stimulation, wherein each stimulation module of the plurality of stimulation modules comprises the corresponding tangential coil.
10. The transcranial magnetic stimulation system according to claim 9, 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, so as 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 the voltage amplitude 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 a 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 stimulating current loop according to a second driving signal after receiving the second driving signal from the control module;
and 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 adjusting signal after receiving the current adjusting signal which is from the control module and is obtained based on the two paths of input signals.
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