CN102727997B - Two 8-shaped cerebral magnetic stimulation coil - Google Patents
Two 8-shaped cerebral magnetic stimulation coil Download PDFInfo
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- CN102727997B CN102727997B CN201210210607.3A CN201210210607A CN102727997B CN 102727997 B CN102727997 B CN 102727997B CN 201210210607 A CN201210210607 A CN 201210210607A CN 102727997 B CN102727997 B CN 102727997B
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Abstract
本发明涉及一种双8字形经颅磁刺激线圈，由第一8字形线圈和第二8字形线圈连接组成，空间上第一8字形线圈和第二8字形线圈的中心重合；且第二8字形线圈的两个半径为Ri的圆形线圈位于对应的第一8字形线圈的两个半径为Ro的圆形线圈内，其中Ro＞Ri。本发明一种双8字形经颅磁刺激线圈，通过在传统8字形线圈内部设置两个半径更小的圆形线圈，并通过布置导体空间位置、内外线圈半径以及内外线圈匝数以提高线圈刺激的聚焦度；刺激范围集中，针对性强，无关神经组织受到刺激的可能性显著降低。
The invention relates to a double-8-shaped transcranial magnetic stimulation coil, which is composed of a first 8-shaped coil and a second 8-shaped coil, and the centers of the first 8-shaped coil and the second 8-shaped coil coincide in space; and the second 8-shaped coil The two circular coils of radius Ri of the figure-shaped coil are located within the corresponding two circular coils of radius Ro of the first figure-eight coil, wherein Ro>Ri. The present invention is a double-8-shaped transcranial magnetic stimulation coil, by arranging two circular coils with smaller radii inside the traditional 8-shaped coil, and by arranging the spatial position of the conductor, the radius of the inner and outer coils, and the number of turns of the inner and outer coils to improve the coil stimulation. The degree of focus; the stimulation range is concentrated, the pertinence is strong, and the possibility of irrelevant nerve tissue being stimulated is significantly reduced.
Description
[technical field]
The invention belongs to transcranial magnetic stimulation technical field, particularly a kind of stevedore knot structure cerebral magnetic stimulation coil.
[background technology]
Transcranial magnetic stimulation (Transcranial magnetic stimulation, be called for short TMS) be a kind of noinvasive biostimulation technology, it utilizes time-varying magnetic field to produce induction field, bioelectric current is caused to conduct in the tissue, and then make nerve fiber, neuron and muscle depolarization, in order to change the action potential of cortical neurogenic cell, affect brain intracellular metabolite and neuroelectricity activity, therefore can in order to treat quite a few neural and mental sickness.The disease that TMS can be utilized to carry out treating at present comprises aphasia, tinnitus, Parkinson's disease, myodystonia, amyotrophic lateral sclerosis (spinal cord) lateral sclerosis, epilepsy, migraine, dysphasia, half side space are ignored, phantom pain, chronic pain, obsession etc.It can also close the activity of specific cortical area in addition, realizes the virtual damage of brain local function.
Transcranial magnetic stimulation instrument can be divided into two parts: pulse current produces circuit and stimulating coil.The parameters of stimulating coil is the core of whole magnetic stimulating device.In order to appointed part can be stimulated accurately and effectively, to the intensity in the magnetic field that coil produces, the degree of depth and degree of focus is stimulated to be proposed very high requirement.On the other hand, from the angle of studying physiological effect, also need the parameters of accurate quantification coil.The degree of focus of Neural stem cell determines the stimulation selective power of magnetic stimulator.High degree of focus can reduce field stimulation, increases and stimulates specific aim, reduces the possibility that irrelevant nervous tissue is upset.The stimulation degree of depth determines the distance that magnetic stimulator can keep certain stimulus intensity.The high degree of depth that stimulates is only had just likely to realize the effective stimulus organized dark cranial nerve.Right existing figure-eight coil (butterfly coil) degree of focus is not enough, and cause field stimulation large, the problem that specific aim is not strong, the probability that irrelevant nervous tissue is upset is large.
[summary of the invention]
The object of the present invention is to provide a kind of two 8-shaped cerebral magnetic stimulation coil with higher degree of focus, improve the effect of transcranial magnetic stimulation, to solve the problem of traditional figure-eight coil degree of focus deficiency.
To achieve these goals, the present invention adopts following technical scheme:
A kind of two 8-shaped cerebral magnetic stimulation coil, is connected to form by the first figure-eight coil and the second figure-eight coil, spatially the center superposition of the first figure-eight coil and the second figure-eight coil; And two radiuses that the circular coil that two of the second figure-eight coil radiuses are Ri is positioned at the first corresponding figure-eight coil are the circular coil of Ro, wherein Ro > Ri.
The present invention further improves and is: Ri:Ro=(0.4 ~ 0.5): 1.
The present invention further improves and is: Ri:Ro=0.5:1.
The present invention further improves and is: the number of turn Ni of the second figure-eight coil is (1 ~ 10) with the ratio of the number of turn No of the first figure-eight coil: 1.
The present invention further improves and is: the first figure-eight coil and the second figure-eight coil are positioned at same plane.
Compared with prior art, the present invention has the following advantages: a kind of two 8-shaped cerebral magnetic stimulation coil of the present invention, by arranging the less circular coil of two radiuses in traditional figure-eight coil inside, and by arrangement of conductors locus, inner-outer coil radius and the inner-outer coil number of turn to improve the degree of focus of coil stimulation; Field stimulation is concentrated, and with strong points, the probability that irrelevant nervous tissue is upset significantly reduces.
[accompanying drawing explanation]
The HPR comparison diagram of figure-eight coil when Fig. 1 is the different stimulated degree of depth and two figure-eight coil (Double-butterflycoil);
Fig. 2 is of the present invention pair of figure-eight coil structure chart;
Fig. 3 is a kind of through the raw circuit diagram of cranium magnetic thorn pulse excitation;
Fig. 4 is the induction field size distribution figure that two 8 wordline circles produce on certain depth;
When Fig. 5 is the different stimulated degree of depth, the graph of a relation of coil HPR and inside and outside umber of turn ratio;
Fig. 6 is outer winding radius when being 3.5cm, the graph of a relation of HPR and Ni/No and Ri/Ro.
[detailed description of the invention]
Below in conjunction with accompanying drawing, the present invention is described in further detail.
Refer to shown in Fig. 2, a kind of two 8-shaped cerebral magnetic stimulation coil of the present invention, connected to form by the figure-eight coil of two different winding radiuses, the figure-eight coil of two different winding radiuses is positioned at same plane, the spatially center superposition of two figure-eight coils, flow through same electric current I in two coils, the effect strengthening center field intensity in center in the same way, is played in electric current I direction.Two 8-shaped cerebral magnetic stimulation coil produces the alternating magnetic field of high degree of focus after being connected to a pulse power under the function of current, may be used for experiment and the treatment of carrying out transcranial magnetic stimulation.The two figure-eight coil of the present invention can use various plain conductor coiling to form, and adopts the mode of not shield electromagnetic to make coil arrangement become Fig. 2 structure.
The two 8-shaped cerebral magnetic stimulation coil of the present invention, compared with traditional figure-eight coil, reaches the object improving degree of focus by arrangement of conductors locus, inner-outer coil radius and the inner-outer coil number of turn.Referring to shown in Fig. 4, is the induction field size distribution that the two 8 wordline circles of the present invention produce on certain depth, can find out that the piezomagnetic theory of the two 8 wordline circles of the present invention is similar with 8 wordline loop-shaped, but main peak is narrower, is conducive to raising degree of focus.Inside and outside two 8-shaped cerebral magnetic stimulation coil, winding radius is respectively Ri, Ro, inside and outside umber of turn is Ni, No, in order to quantize degree of focus, introduce half values of powers region (Half Power Region, HPR), namely electric field magnitude is the area in the region formed a little at maximum decay-3dB place, and HPR is less, then degree of focus is better.The degree of focus of more two 8-shaped cerebral magnetic stimulation coil and figure-eight coil, calculate the HPR value in the different stimulated degree of depth, wherein, the radius of figure-eight coil is 3.5cm, and the number of turn is 4 circles; Two 8-shaped cerebral magnetic stimulation coil selects parameters optimization, i.e. Ro=3.5cm, Ri=2cm, No=4, Ni=8, and result as shown in Figure 1; When stimulating the degree of depth to change from 1cm to 4cm, the HPR of two 8-shaped cerebral magnetic stimulation coil is less than 8-shaped all the time, illustrates that the degree of focus of two 8-shaped cerebral magnetic stimulation coil is better than the degree of focus of figure-eight coil.
Provide some references at this, such as, get Ro=3.5cm, Ri=2.0cm, stimulate depth H to get 2.0cm respectively, 3.0cm and 4.0cm, I=5kA, f=10kHz, Ni/No get 1 to 10.HPR result is as shown in Figure 5, visible, and stimulate the degree of depth darker, HPR is larger, and degree of focus is poorer; When inside and outside umber of turn ratio increases, its HPR reduces, but the speed reduced increases with the number of turn and slows down, and therefore, in order to improve the degree of focus of two figure-eight coil as far as possible, should make interior umber of turn slightly more than outer umber of turn.If get Ro=3.5cm, H=3.0cm, I=5kA, f=10kHz, Ni/No get 1 to 10, Ri/Ro and get 0.1 to 0.9, as shown in Figure 6, for certain Ni/No, when Ri/Ro close to 0.5 time, HPR obtains minima.Ni/No close to 10 time, make HPR obtain the Ri/Ro of optimal value close to 0.4, when Ni/No close to 1 time, make HPR obtain the Ri/Ro of optimal value close to 0.5.In order to reach best degree of focus, suggestion adopts Ri/Ro=0.5.
Length and the method for arranging of lead-in wire will be noted when coil being connected to pulse generating circuit, as far as possible simple, in order to avoid have influence on coil effect.Provide a kind of pulse generating circuit at this, as shown in Figure 3, L is two figure-eight coils; C is charging capacitor, and R is current-limiting resistance, and D is commutation diode, and these elements constitute rectification charging loop.The control signal sent by control circuit triggers turn on thyristors, makes electric capacity to coil discharge, produces sinusoidal single-pulse current, for transcranial magnetic stimulation.
Claims (1)
1. a two 8-shaped cerebral magnetic stimulation coil, is characterized in that, connected to form, spatially the center superposition of the first figure-eight coil and the second figure-eight coil by the first figure-eight coil and the second figure-eight coil; And two radiuses that the circular coil that two of the second figure-eight coil radiuses are Ri is positioned at the first corresponding figure-eight coil are the circular coil of Ro, wherein Ro > Ri; Ri:Ro=0.5:1; The number of turn Ni of the second figure-eight coil is 1 ~ 10:1 with the ratio of the number of turn No of the first figure-eight coil; First figure-eight coil and the second figure-eight coil are positioned at same plane; Flow through same electric current I in first figure-eight coil and the second figure-eight coil, electric current I direction in center in the same way; It is in parallel with charging capacitor C when described pair of 8-shaped cerebral magnetic stimulation coil uses; The secondary of transformator is in series with current-limiting resistance R, commutation diode D and charging capacitor C successively; The IGCT two 8-shaped cerebral magnetic stimulation coil discharged for controlling charging capacitor C is connected with, described IGCT connection control circuit between two 8-shaped cerebral magnetic stimulation coil and charging capacitor C.
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| CN201210210607.3A CN102727997B (en) | 2012-06-25 | 2012-06-25 | Two 8-shaped cerebral magnetic stimulation coil |
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Families Citing this family (10)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| CN105435371A (en) * | 2015-12-17 | 2016-03-30 | 天津大学 | 8-shaped coil transcranial magnetic stimulation system based on magnetic resonant coupling principle |
| CN106075730B (en) * | 2016-06-07 | 2018-06-12 | 成都信息工程大学 | It is a kind of to join the electromagnetic excitation method for realizing time-scale extension with multiple activation source level |
| CN107469233A (en) * | 2017-08-30 | 2017-12-15 | 天津大学 | Quatrefoil coil transcranial magnetic stimulation system based on magnetic resonance coupling principle |
| US11000693B2 (en) | 2018-02-20 | 2021-05-11 | Neuronetics, Inc. | Magnetic stimulation coils and ferromagnetic components for treatment and diagnostic procedures |
| EP3755422A4 (en) * | 2018-02-20 | 2021-09-29 | Neuronetics, Inc. | MAGNETIC STIMULATION COILS AND FERROMAGNETIC COMPONENTS FOR TREATMENT AND DIAGNOSIS |
| CN109621209A (en) * | 2018-12-29 | 2019-04-16 | 北京神畅科技发展有限公司 | A kind of inside and outside reversal circle cerebral magnetic stimulation coil |
| CN113440731B (en) * | 2021-08-11 | 2022-02-15 | 成都理工大学 | Asymmetrical shaped coil for cranial electromagnetic stimulation and craniocerebral electromagnetic stimulation system |
| CN113679950A (en) * | 2021-08-30 | 2021-11-23 | 华南理工大学 | 8-shaped transcranial magnetic stimulation coil, magnetic stimulation device and magnetic stimulation system |
| CN114028720A (en) * | 2021-12-31 | 2022-02-11 | 湖南华医电磁医学研究院有限公司 | A magnetic stimulation device |
| CN114177532A (en) * | 2021-12-31 | 2022-03-15 | 湖南华医电磁医学研究院有限公司 | Cooling device for magnetic stimulation system and magnetic stimulation system |
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| Publication number | Priority date | Publication date | Assignee | Title |
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| CN101869478A (en) * | 2009-04-24 | 2010-10-27 | 株式会社东芝 | MR imaging apparatus and radio-frequency coil |
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| US20050154426A1 (en) * | 2002-05-09 | 2005-07-14 | Boveja Birinder R. | Method and system for providing therapy for neuropsychiatric and neurological disorders utilizing transcranical magnetic stimulation and pulsed electrical vagus nerve(s) stimulation |
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| Publication number | Priority date | Publication date | Assignee | Title |
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| CN101869478A (en) * | 2009-04-24 | 2010-10-27 | 株式会社东芝 | MR imaging apparatus and radio-frequency coil |
Non-Patent Citations (2)
| Title |
|---|
| 磁刺激8字形线圈的结构对感应电磁分布影响;王修信等;《北京生物医学工程》;20060430;第25卷(第2期);第193-195页 * |
| 经颅磁刺激线圈半径对深度感应电场分布影响;王修信等;《广西物理》;20041008;第25卷(第4期);第6-8页 * |
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