CN104096316A - H-shaped coil optimization method for deep brain transcranial magnetic stimulation - Google Patents
H-shaped coil optimization method for deep brain transcranial magnetic stimulation Download PDFInfo
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- 238000000034 method Methods 0.000 title claims abstract description 27
- 238000011491 transcranial magnetic stimulation Methods 0.000 title claims abstract description 19
- 210000004556 brain Anatomy 0.000 title claims abstract description 18
- 238000005457 optimization Methods 0.000 title claims abstract description 17
- 210000003715 limbic system Anatomy 0.000 claims abstract description 45
- 230000005684 electric field Effects 0.000 claims abstract description 39
- 230000002360 prefrontal effect Effects 0.000 claims abstract description 21
- 238000013461 design Methods 0.000 claims abstract description 10
- 239000004020 conductor Substances 0.000 claims description 25
- 230000002093 peripheral effect Effects 0.000 claims description 8
- 230000000638 stimulation Effects 0.000 claims description 8
- 238000005481 NMR spectroscopy Methods 0.000 claims description 6
- 230000004936 stimulating effect Effects 0.000 claims description 4
- 238000004364 calculation method Methods 0.000 claims description 3
- 230000011218 segmentation Effects 0.000 claims description 3
- 238000002595 magnetic resonance imaging Methods 0.000 abstract 1
- 210000003128 head Anatomy 0.000 description 75
- 210000001652 frontal lobe Anatomy 0.000 description 5
- 238000005516 engineering process Methods 0.000 description 4
- 210000004761 scalp Anatomy 0.000 description 4
- 230000002490 cerebral effect Effects 0.000 description 3
- 238000010276 construction Methods 0.000 description 2
- 230000000694 effects Effects 0.000 description 2
- 210000001320 hippocampus Anatomy 0.000 description 2
- 230000006698 induction Effects 0.000 description 2
- 238000011160 research Methods 0.000 description 2
- 238000013459 approach Methods 0.000 description 1
- 210000005252 bulbus oculi Anatomy 0.000 description 1
- 238000011161 development Methods 0.000 description 1
- 230000018109 developmental process Effects 0.000 description 1
- 210000002451 diencephalon Anatomy 0.000 description 1
- 230000008451 emotion Effects 0.000 description 1
- 230000005284 excitation Effects 0.000 description 1
- 210000000887 face Anatomy 0.000 description 1
- 230000002197 limbic effect Effects 0.000 description 1
- 230000015654 memory Effects 0.000 description 1
- 210000001259 mesencephalon Anatomy 0.000 description 1
- 210000000478 neocortex Anatomy 0.000 description 1
- 210000005036 nerve Anatomy 0.000 description 1
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Abstract
The invention discloses an H-shaped coil optimization method for deep brain transcranial magnetic stimulation. The H-shaped coil optimization method for deep brain transcranial magnetic stimulation comprises the following steps of: establishing a real head structure model containing a limbic system through magnetic resonance imaging or CT data, and establishing a real head conductivity model containing a limbic system in finite element software; establishing an H-shaped coil tangential with the outer surface of the real head structure model according to the outline of the real head structure model; determining the distribution ranges of the conductive wire models of the prefrontal, top and side, and establishing H-shaped coil models in the different conductive wire gaps of the prefrontal, top and side of the real head structure model; simulating the electric field distribution of the H-shaped coil on the real head conductivity model by applying a finite element method, and setting standards for evaluating the deep features of the coil; determining the optimal conductive wire gaps of the different positions of the prefrontal, top and side of the H-shaped coil according to the standards of the design of the H-shaped coil. According to the H-shaped coil optimization method for deep brain transcranial magnetic stimulation disclosed by the invention, the conductive wire gaps of the prefrontal, top and side are changed, and the influence of the conductive wire gaps on the deep features of the electric field is evaluated.
Description
Technical field
The present invention relates to a kind of H type coil for brain deep transcranial magnetic stimulation.Particularly relate to a kind of H type coil optimization method for brain deep transcranial magnetic stimulation based on true head conductivity model.
Background technology
Transcranial magnetic stimulation technology is a kind of painless, noinvasive, non-invasive technology, and the magnetic signal that the pulse current in coil produces can see through skull undampedly and stimulate to cerebral nerve.Along with research deeply, the development of technology, the stimulation of shallow-layer can not meet the demand of medical treatment and scientific research, deep stimulation is arisen at the historic moment.Current coil can only stimulate the peripheral cortex region to 1.5-2cm.Deep stimulates in not increasing excitation, meets the stimulation to cerebral deep structure, reduces the damage to peripheral cortex.
H type coil has complicated structural design, and base portion is to stimulate major part, the tangential scalp of wire direction; Outstanding loop and link circuit, away from stimulation target, weaken the impact on target area.But current H type coil designs based on Sphere Model, there is larger difference in Sphere Model and true head structure.The accuracy of head model affects the electric field distribution law that transcranial magnetic stimulation coil produces on model.True head mould is for the design of H type coil provides foundation, and the Electric Field Distribution that coil is produced at head more levels off to truth.
H type coil utilizes the vector superposed principle of induction field, strengthens the induction field in the target tissue of deep; Base portion wire is certain intervals and distributes, and reduces the stimulus intensity of peripheral cortex with this.Conductor spacing and distribution influence electric field intensity and the deep characteristic of peripheral cortex.It is far from being enough that the attenuation characteristic of electric field on a certain line segment only studied in the complexity explanation of head and H type coil, needs more detailed internal electric field distributed intelligence.Comprise Hippocampus, the information exchange of the isostructural limbic system of corpus amygdaloideum between midbrain, diencephalon and neopallium structure plays an important role, be necessary limbic system to separate, set up comprise limbic system true head model.The present invention adopts the method for finite element to calculate head Electric Field Distribution, the impact of the H type coil conductor spacing of assessment prefrontal, top and sidepiece on deep characteristic.
Summary of the invention
Technical problem to be solved by this invention is, provide a kind of by changing the conductor spacing of prefrontal, top and sidepiece, use the method simulate electric field of finite element at the H type coil optimization method for brain deep transcranial magnetic stimulation of distribution situation and the deep characteristic of true conductivity model.
The technical solution adopted in the present invention is: a kind of H type coil optimization method for brain deep transcranial magnetic stimulation, use the method simulate electric field of finite element in distribution situation and the deep characteristic of true head conductivity model, optimize the conductor spacing of prefrontal, top and sidepiece, weaken head shallow-layer electric field intensity, increase head deep layer electric field intensity, comprise following steps:
1) set up by nuclear magnetic resonance or CT data the true head structural model that comprises limbic system, in finite element software, set up the true head conductivity model that comprises limbic system;
2) set up the H type coil of tangential described true head structural model outer surface according to the outline of true head structural model; Consider structure and the position characteristics of head edge system, determine prefrontal, top and sidepiece lead model distribution, be based upon the H type coil model at prefrontal, top and the sidepiece different conductor interval of true head structural model;
3) use the Electric Field Distribution of finite element method for simulating H type coil on true head conductivity model, the standard of evaluating coil deep characteristic be set, comprising:
(1) in finite element software, divide by grid, true head conductivity model is divided into limited unit, foundation can apply to the FEM (finite element) model of numerical computations; In FEM (finite element) model, load and solve, obtain the Electric Field Distribution of H type coil on true head model;
(2) object stimulating in order to meet deep, reduce the stimulation to peripheral cortex simultaneously, adopt the standard of evaluating the design of H type coil that is compared to of true head conductivity model surface field maximum and true head conductivity model limbic system electric field maximum;
4) taking the standard of evaluating H type coil design as foundation, determine the best conductor spacing of H type coil prefrontal, top and sidepiece diverse location.
Step 1) the described foundation head model that comprises DEEP STRUCTURE comprises:
(1) by nuclear magnetic resonance or the interactively medical image control system of CT data importing, comprise Threshold segmentation, region growing and the operation of manually modifying, extract the edge of head and limbic system, set up respectively the three-dimensional patch model of head and the three-dimensional patch model of limbic system;
(2) in finite element software, be head physical model and limbic system physical model by three-dimensional head patch model and the three-dimensional dough sheet model conversation of limbic system, described head physical model and limbic system physical model are overlapped to Boolean calculation, the true head structural model that foundation comprises limbic system, carry out electrical conductivity assignment, set up the true head conductivity model that comprises limbic system.
Step 2) described H type coil model, be to adopt pulling mode to set up, the conductor cross-section of H type coil model is that the length of side is the square of 1mm, conductor spacing true head structural model surface 5mm.
Described pulling mode is to carry out described point line according to true head conductivity model outline in finite element software, form the path on tangential true head conductivity model top layer, set up a cross section perpendicular to path, pull described cross section along path, obtain the H type coil model on tangential true head conductivity model top layer.
Step 3) described true head conductivity model surface field maximum is less with the ratio of true head conductivity model limbic system electric field maximum, represents that H type coil depth characteristic is better.
A kind of H type coil optimization method for brain deep transcranial magnetic stimulation of the present invention, sets up the threedimensional model of head and limbic system by MRI or CT data.The construction features of CONSIDERING EDGE system, the conductor spacing of change prefrontal, top and sidepiece, the impact of assessment conductor spacing on electric field deep characteristic.Due to the complexity of head construction, it is slightly variant that the wire of different interval produces Electric Field Distribution, therefore adopts the standard of evaluating coil deep characteristic that is compared to of true head conductivity model surface field maximum and limbic system maximum.
Brief description of the drawings
Fig. 1 is the flow chart of the inventive method;
Fig. 2 is head model and the H type coil model that adopts method of the present invention to set up.
In figure
1:H type coil model 2: frontal lobe top wire
3: prefrontal wire 4: frontal lobe sidepiece wire
Detailed description of the invention
Below in conjunction with embodiment and accompanying drawing, a kind of H coil optimization method for brain deep transcranial magnetic stimulation of the present invention is described in detail.
H type coil is used for stimulating the DEEP STRUCTURE of brain, and cerebral limbic system is made up of structure under limbic lobe and relevant cortex and cortex, relevant with higher nervous activities such as emotion, spirit, memories.Due to the difference of arrangement of conductors, in limbic system, produce different effects.In order to reach the darker stimulation degree of depth, reduce the electric field intensity of top layer scalp simultaneously.H type coil conductor spacing to prefrontal and top and sidepiece is optimized.
As shown in Figure 1, a kind of H type coil optimization method for brain deep transcranial magnetic stimulation of the present invention, use the method simulate electric field of finite element in distribution situation and the deep characteristic of true conductivity model, optimize before frontal lobe, above and the conductor spacing of side, weaken head shallow-layer electric field intensity, increase head deep layer electric field intensity, comprise following steps:
1) set up by nuclear magnetic resonance (MRI) or CT data the true head structural model that comprises limbic system, in finite element software, set up the true head conductivity model that comprises limbic system;
The head model that described foundation comprises DEEP STRUCTURE comprises:
(1) by nuclear magnetic resonance or the interactively medical image control system of CT data importing (Mimics), comprise Threshold segmentation, region growing and the operation of manually modifying, extract the edge of head and limbic system.After three-dimensional surface modeling, the model obtaining does not pass through any optimization, do not affecting on the basis of head model structure, adopt smooth operation to come level and smooth solid surface, simplify operation by dough sheet and reduce tri patch quantity, set up respectively the three-dimensional patch model of head and the three-dimensional patch model of limbic system;
(2) in finite element software, be head physical model and limbic system physical model by three-dimensional head patch model and the three-dimensional dough sheet model conversation of limbic system, described head physical model and limbic system physical model are overlapped to Boolean calculation, ensure node and unit on two physical model Border faces, the true head structural model that foundation comprises limbic system, carry out electrical conductivity assignment, set up the true head conductivity model that comprises limbic system.
2) set up the H type coil on tangential described true head structural model surface according to the outline of true head structural model; H type coil is positioned at prefrontal and top conductor line mainly stimulates the anterior cingutate of limbic system; H type coil is positioned at frontal lobe sidepiece wire mainly stimulates the structure such as Hippocampus, corpus amygdaloideum.Consider structure and the position characteristics of head edge system, determine prefrontal, top and sidepiece lead model distribution, the lower edge of H type coil is positioned at the top of head brow ridge, weakens the impact on eyeball of electric field that H type coil forms.Be based upon the H type coil model at prefrontal, top and the sidepiece different conductor interval of true head structural model.
Described H type coil model, be to adopt pulling mode to set up, the conductor cross-section of H type coil model is that the length of side is the square of 1mm, in analog simulation, consider the impact of true coil case and experimenter's hair, H type coil is apart from the surperficial 5mm of true head structural model.Described pulling mode is to consider that H type coil is positioned at frontal lobe part wire and needs tangential scalp, in finite element software, carry out described point line according to true head structural model outline, form the path on tangential true head conductivity model top layer, set up a cross section perpendicular to path, pull described cross section along path, obtain the H type coil model on tangential true head structural model top layer.
3) use the Electric Field Distribution of finite element method for simulating H type coil on true head conductivity model, the standard of evaluating coil deep characteristic be set, comprising:
(1) in finite element software, divide by grid, true head conductivity model is divided into limited unit, foundation can apply to the FEM (finite element) model of numerical computations; In FEM (finite element) model, load and solve, obtain the Electric Field Distribution of H type coil on true head model.
(2) object stimulating in order to meet deep reduces the stimulation to peripheral cortex simultaneously, adopts scalp electric field magnitude and the ratio of limbic system electric field magnitude to can be used as the standard of evaluating the modelling of H type coil.Due to the difference of H type coil conductor spacing, its Electric Field Distribution of bringing out on true head conductivity model is slightly variant, therefore utilize the deep evaluating characteristics standard that is compared to of true head electrical conductivity top layer electric field maximum and true head conductivity model limbic system maximum, evaluate the standard of H type coil design.Described true head conductivity model surface field maximum is less with the ratio of true head conductivity model limbic system electric field maximum, represents that H type coil depth characteristic is better.
4) taking the standard of evaluating H type coil design as foundation, determine the best conductor spacing of H type coil prefrontal, top and sidepiece diverse location.In different H type coil conductor spacings, the electric field producing on true head conductivity model at H type coil reaches threshold value, if true head conductivity model surface field maximum approaches with the ratio of true head conductivity model limbic system electric field maximum, true head conductivity model surface field smaller is excellent, illustrate under identical depth characteristic, the H type coil model of this conductor spacing is less on the impact of head peripheral cortex.
Claims (5)
1. the H type coil optimization method for brain deep transcranial magnetic stimulation, it is characterized in that, use the method simulate electric field of finite element in distribution situation and the deep characteristic of true head conductivity model, optimize the conductor spacing of prefrontal, top and sidepiece, weaken head shallow-layer electric field intensity, increase head deep layer electric field intensity, comprise following steps:
1) set up by nuclear magnetic resonance or CT data the true head structural model that comprises limbic system, in finite element software, set up the true head conductivity model that comprises limbic system;
2) set up the H type coil of tangential described true head structural model outer surface according to the outline of true head structural model; Consider structure and the position characteristics of head edge system, determine prefrontal, top and sidepiece lead model distribution, be based upon the H type coil model at prefrontal, top and the sidepiece different conductor interval of true head structural model;
3) use the Electric Field Distribution of finite element method for simulating H type coil on true head conductivity model, the standard of evaluating coil deep characteristic be set, comprising:
(1) in finite element software, divide by grid, true head conductivity model is divided into limited unit, foundation can apply to the FEM (finite element) model of numerical computations; In FEM (finite element) model, load and solve, obtain the Electric Field Distribution of H type coil on true head model;
(2) object stimulating in order to meet deep, reduce the stimulation to peripheral cortex simultaneously, adopt the standard of evaluating the design of H type coil that is compared to of true head conductivity model surface field maximum and true head conductivity model limbic system electric field maximum;
4) taking the standard of evaluating H type coil design as foundation, determine the best conductor spacing of H type coil prefrontal, top and sidepiece diverse location.
2. a kind of H type coil optimization method for brain deep transcranial magnetic stimulation according to claim 1, is characterized in that step 1) the described foundation head model that comprises DEEP STRUCTURE comprises:
(1) by nuclear magnetic resonance or the interactively medical image control system of CT data importing, comprise Threshold segmentation, region growing and the operation of manually modifying, extract the edge of head and limbic system, set up respectively the three-dimensional patch model of head and the three-dimensional patch model of limbic system;
(2) in finite element software, be head physical model and limbic system physical model by three-dimensional head patch model and the three-dimensional dough sheet model conversation of limbic system, described head physical model and limbic system physical model are overlapped to Boolean calculation, the true head structural model that foundation comprises limbic system, carry out electrical conductivity assignment, set up the true head conductivity model that comprises limbic system.
3. a kind of H type coil optimization method for brain deep transcranial magnetic stimulation according to claim 1, it is characterized in that, step 2) described H type coil model, to adopt pulling mode to set up, the conductor cross-section of H type coil model is that the length of side is the square of 1mm, conductor spacing true head structural model surface 5mm.
4. a kind of H type coil optimization method for brain deep transcranial magnetic stimulation according to claim 3, it is characterized in that, described pulling mode is to carry out described point line according to true head conductivity model outline in finite element software, form the path on tangential true head conductivity model top layer, set up a cross section perpendicular to path, pull described cross section along path, obtain the H type coil model on tangential true head conductivity model top layer.
5. a kind of H type coil optimization method for brain deep transcranial magnetic stimulation according to claim 1, it is characterized in that, step 3) described true head conductivity model surface field maximum is less with the ratio of true head conductivity model limbic system electric field maximum, represents that H type coil depth characteristic is better.
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Cited By (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN105572488A (en) * | 2015-12-31 | 2016-05-11 | 中国医学科学院生物医学工程研究所 | System used for detecting encephalic induced electric field induced by transcranial magnetic stimulation, and manufacturing method |
| CN109200472A (en) * | 2018-10-15 | 2019-01-15 | 中国医学科学院生物医学工程研究所 | Regulate and control the method and device of H coil encephalic field distribution by conducting block magnetic inductive block |
| CN110491669A (en) * | 2019-06-07 | 2019-11-22 | 中国医学科学院生物医学工程研究所 | A kind of H-type coil winding and fixed device and its application method |
| JP2021512690A (en) * | 2018-02-05 | 2021-05-20 | ブレインズウェイ リミテッド | Electromagnetic coil assembly |
| CN113332601A (en) * | 2015-10-28 | 2021-09-03 | 诺沃库勒有限责任公司 | TTFIELD therapy with electrode position optimization on the head based on MRI-based conductivity measurements |
Citations (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN101488297A (en) * | 2009-02-24 | 2009-07-22 | 中国医学科学院生物医学工程研究所 | Head simulation model used for brain nerve magnetic stimulation induction electric field detection |
| WO2014022236A1 (en) * | 2012-07-30 | 2014-02-06 | Neuroprex Inc. | Devices and methods for magnetic stimulation for the treatment of neurological disorders |
-
2014
- 2014-07-21 CN CN201410346305.8A patent/CN104096316B/en active Active
Patent Citations (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN101488297A (en) * | 2009-02-24 | 2009-07-22 | 中国医学科学院生物医学工程研究所 | Head simulation model used for brain nerve magnetic stimulation induction electric field detection |
| WO2014022236A1 (en) * | 2012-07-30 | 2014-02-06 | Neuroprex Inc. | Devices and methods for magnetic stimulation for the treatment of neurological disorders |
Non-Patent Citations (2)
| Title |
|---|
| NIKOLAOS J.TACHAS等: "The Effect of Coil Modeling on the Predicted Induced Electric Field Distribution During TMS", 《IEEE TRANSACTIONS ON MAGNETICS》 * |
| 程欢欢等: "深部磁刺激线圈脑内电场分布的仿真研究", 《天津市生物医学工程学会第三十四届学术年会论文集》 * |
Cited By (8)
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|---|---|---|---|---|
| CN113332601A (en) * | 2015-10-28 | 2021-09-03 | 诺沃库勒有限责任公司 | TTFIELD therapy with electrode position optimization on the head based on MRI-based conductivity measurements |
| CN105572488A (en) * | 2015-12-31 | 2016-05-11 | 中国医学科学院生物医学工程研究所 | System used for detecting encephalic induced electric field induced by transcranial magnetic stimulation, and manufacturing method |
| JP2021512690A (en) * | 2018-02-05 | 2021-05-20 | ブレインズウェイ リミテッド | Electromagnetic coil assembly |
| JP7153949B2 (en) | 2018-02-05 | 2022-10-17 | ブレインズウェイ リミテッド | electromagnetic coil assembly |
| CN109200472A (en) * | 2018-10-15 | 2019-01-15 | 中国医学科学院生物医学工程研究所 | Regulate and control the method and device of H coil encephalic field distribution by conducting block magnetic inductive block |
| CN109200472B (en) * | 2018-10-15 | 2022-02-01 | 中国医学科学院生物医学工程研究所 | Method and device for regulating and controlling intracranial field distribution of H coil through conductive block and magnetic conductive block |
| CN110491669A (en) * | 2019-06-07 | 2019-11-22 | 中国医学科学院生物医学工程研究所 | A kind of H-type coil winding and fixed device and its application method |
| CN110491669B (en) * | 2019-06-07 | 2021-08-10 | 中国医学科学院生物医学工程研究所 | H-shaped coil winding and fixing device and using method thereof |
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