CN1093937A - 神经磁刺激的方法和装置 - Google Patents
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Abstract
一种超声和磁结合的刺激神经组织的方法和装
置,利用一产生磁感应强度B的磁场发生装置,使磁
场作用于被刺激的皮下神经组织,以及一超声波发射
装置,同时发射超声波,并聚焦于上述磁场区,该超声
波的振动方向与磁场方向正交,从而在被刺激的皮下
组织内产生一直径约1cm的刺激焦点区,以便集中
于某一神经束或某一特定的中枢区域,而避免刺激邻
近的组织。
Description
本发明涉及功能性神经肌肉或神经磁刺激(neuromagnetic)的方法和装置,其中磁场作用于皮下待刺激的组织。
近来功能性神经刺激技术,尤其是非接触的磁刺激方法有了很大发展。临床上,在神经科和康复医学领域,以及对中枢和外周神经的无创功能性刺激,都有应用实例。然而,由于不可能把磁场聚焦到小于一立方厘米的区域,而正是这样的刺激区域才具有重要的临床应用价值,磁刺激方法的有效性和特异性才受到很大限制。临床应用时需将大约一特斯拉这样相当强的磁场聚焦到一根神经束或某一神经区域,例如聚焦到皮层前区的大拇指运动中枢,否则,距此仅大约一厘米的食指区域将会受到不希望的刺激。
本发明的目的是提供一种新颖的神经刺激方法和装置。
本发明的其次目的是克服常用磁刺激方法固有的聚焦问题。
本发明的进一步目的在于对皮下组织实现精确聚焦刺激。
上述目的是依靠下述新方法和装置来实现的。将磁感应强度为B的磁场作用于含有待刺激神经的生物组织上,同时将聚焦的超声波束与磁场叠加,超声波在皮下组织中形成直径大约为一厘米的焦点,并沿着与磁场正交的方向振动。
基于本发明的方法和装置,由产生磁场的装置和产生聚焦超声波的装置构成,其中前者产生磁感应强度为B的磁场并作用于生物组织上,后者同时发射聚焦的超声束于待刺激部位,在皮下组织中形成直径大约为1厘米的焦点,并且超声波的振动方向和磁场方向正交。
根据这一发明,具有磁感应强度B的磁场与聚焦的超声波同时作用于待刺激部位以产生直径约1厘米的刺激焦点,其中超声波由单脉冲或脉冲串列组成,频率范围在0.2到3MHz之间,特别适合的频率范围是0.3-0.5MHz。所加的磁感应强度为B的磁场,其波形可以是直流,也可选用单脉冲或脉冲列。
在本发明中,超声波和磁场在焦点处叠加具有相当大的优点使得刺激仅仅发生在一根神经束或某一特定的中枢区域而避免邻近的组织受到不应有的刺激。
本发明的目的和优点详见附图及实施例说明:
图1:超声波源和神经组织的截面图
图2:组织中超声波焦点的横截面,即x-y平面
图3:实现本发明的仪器装置框图
根据图1,可聚焦的超声波源1发射超声波2进入组织3,在皮下组织中与主辐射轴z正交的主向上产生大约直径为1厘米的焦点5。这一点目前很容易在0.2到3MHz特别是在0.3到0.5MHz的频率范围内实现,只要超声波的功率强度Pus在焦点处足够大,生物组织的粒子就会以超声波的频率振动。神经组织中的带电粒子,特别是电子,将会形成对应的交变电流J。与此同时,在与超声波振动(或电流J方向)正交的方向上加入磁感应强度为B的磁场,将产生洛伦兹(Lorentzin)力F,其方向与B及J皆正交。当然,B可以是直流也可选用脉冲磁场。图2表示一恒磁场B与聚焦超声波即时作用,在x>0区域产生负电荷积累,在x<0的区域产生对应等量的正电荷。两种电荷区域之间产生的电位差2V由下式决定:
V=B·Dus·Uz (1)
式中Dus表示超声波焦点5的横截面直径,Uz表示超声波引起的电荷载体的振动速度,其与超声波的功率强度Pus、组织密度rho及超声波穿过组织的速度Cus有关:
我们用下面的例子作一定量估算:
rho=1000Kg/m
Cus=1500m/sec
B=1Tesla
Pus=2000W/cm
Dus=0.01m
f=0.5MHz
利用公式(1)、(2)计算感应电压V:
=103mV,
此电压将导致细胞模除极化。我们假设所采用的超声波频率为0.5MHz,则有波长为
λ=cus/f=(1500m/sec)/0.5·106Hz=3mm.(3)
理论上有可能获得小到直径为
Dus=λ/2=1.5mm。 (4)
的焦点,因此,实际上并不难获得1厘米直径的焦点。
图2中的横截面10即x-y平面表示图1中的超声波焦点5,而超声波所作用的这个横截面10表明,正电荷载体集中的区域12引起除极化即刺激,这一区域和负电载体集中的另一区域14皆由超声波和磁场B即时作用而产生。
多个脉冲可以显著增加刺激电压的脉宽从而降低神经的兴奋阈值。图2中的正电荷区域在x方向将扩展Dmag=0.4.Dus=4毫米(3db点),甚至到数厘米深处,该Dmag值仍然保持聚焦精确度,使得该方法的刺激范围比常用的磁刺激方法更准确。
为了进一步增加聚焦的准确性,可以用CAT、MRI或超声波诊断仪器输出的解剖图象信息控制超声阵元的输出幅度和相位。
为了获得最佳的刺激效果,需要调节所加超声波和磁场的波形及相位关系。我们由电场E亦即感应电压沿x的一阶导数来证明:
式中λ是超声在生物组织中传播的波长。现在我们应用同频率f的正弦磁场By
By=Bo·cos(2πft-α). (6)
合并(5)、(6)两式,得
Ex=- (dV)/(dx)
α= (2πZo)/(λ) +2nπ,(n=integernumber) (8)
时,电场︱Ex︱在焦点(Z=Z0)附近达到最大值:
=Emax·cos2(2πft-2πz/λ) (9)
(9)式表明,当交变磁场和超声波在焦点处同步时产生的感应电场是一最大值在焦点的驻波,且方向不变,其值是非同步时的两倍,有利于刺激神经。
图3是实现同步刺激的基本实验装置示意图,其中超声波源1将超声波2聚焦到焦点5,驱动器16和17分别驱动超声波源1和线圈7以产生超声波2和磁场B。同步器18和延迟线路19对频率和相位进行控制。调整延迟量可以改变刺激点从而使该方法具有高的选择性。除正弦波形外,也可以选用脉冲或脉冲串列形式的磁场和超声波,同样要求同步,即同频率和同相位以产生最大的电场。
在临床上应用该技术对重要的脑区域刺激时,首先会遇到这样两个主要问题:
(1)颅骨将衰减10到20db的入射超声波;
(2)颅骨内的各种反射会导致不希望的二次聚焦。
对此,可用数个在头上形成头盔状的超声波聚焦系统加以克服。这样的方法能成倍地提高焦点处的功率强度而不增加焦点前的能量消耗。通过CAT、MRI或超声波诊断仪器的输出构成的反馈以及前述幅度和相位控制方法也可一并使用以进一步减小二次聚焦。
由于聚焦主要是由超声波完成的,所以可以设计大线圈以便产生强磁场。与常用的磁刺激方法相比较,这样做并不会降低系统的聚焦性能。
为了进一步减小焦点前的可能刺激,本发明还能借用类似于脑磁图和心磁图测量中的多通道系统,采用多线圈产生所需要的磁场。
超声波产生不稳定空化的可能性随着超声的功率增加而增加。对于大部分组织部位其阈值大约为每平方厘米6000瓦特,因此该方法中所选的上限超声波功率强度每平方厘米2000瓦特,远低于这一阈值,在安全范围之内。
聚焦超声波的热效应已在临床上用于热疗。如果忽略热量在组织的传导,则由超声波引起的组织温升dT/dt为:
dT/dt=2α·Pus/(rho.cm) (10)
设选用超声波频率为0.5MHz,其它典型参数为:
超声波衰减系数α=0.015/厘米
组织比热 Cm=4.2焦尔/(gk)
计算表明,宽1毫秒频率为0.5MHz的超声波脉冲引起的组织温升大约为0.014K,显然可以忽略。
本发明发展了神经磁刺激技术,利用超声波和磁结合刺激神经组织,其中磁场作用于生物组织,同时将超声聚焦于待刺激的部位,在焦点处二者方向正交,产生的刺激场聚焦在大约直径1厘米的范围内,以便集中于某一神经束或某一特定的中枢区域,而避免刺激邻近的组织。
Claims (12)
1、一种神经磁刺激方法,包括步骤如下:
对一欲刺激的皮下神经组织施加一具有磁感应强度B的磁场,
将一超声波束聚焦至所述磁场区,并使该超声波振动方向与所述磁场方向正交,
从而使上述刺激场聚焦于欲刺激的皮下组织内,其焦点直径约为1cm。
2、如权利要求1所述的方法,其特征在于所述超声波的频率在0.2到3MHz范围内,最佳范围为0.3到0.5MHz。
3、如权利要求1所述的方法,其特征在于所述超声波以单脉冲方式工作。
4、如权利要求1所述的方法,其特征在于所述超声波以脉冲串列的方式工作。
5、如权利要求1所述的方法,其特征在于所述超声波的幅度和相位受到控制。
6、如权利要求1所述的方法,其特征在于可由多个超声波聚焦束同时施加到一个皮下焦点处。
7、如权利要求1所述的方法,其特征在于所述磁场可为直流场。
8、如权利要求1所述的方法,其特征在于所述磁场可以由单脉冲或脉冲串列形成。
9、如权利要求1所述的方法,其特征在于所述磁场和所述超声波在所述聚焦区的相位和频率相同。
10、一种神经磁刺激装置,包括一可对欲刺激的皮下神经组织施加具有磁感应强度B的磁场的装置,一超声波发射装置,将聚焦超声波束同时发射到所述磁场区,并且该超声波的振动方向与所述磁场方向正交,
从而在皮下组织内产生一聚焦刺激,其焦点直径约为1cm。
11、如权利要求10所述的装置,其特征在于所述超声波发射装置的工作频率在0.2到3MHz范围内,最佳频率范围为0.3到0.5MHz。
12、如权利要求10所述的装置,其特征在于具有多个超声波发射装置,所发射的超声波聚焦至所述磁场区。
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CN111568372A (zh) * | 2020-04-08 | 2020-08-25 | 深圳市神经科学研究院 | 超声刺激磁共振成像同步方法和装置 |
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CN113101526B (zh) * | 2021-04-12 | 2024-09-27 | 中国医学科学院生物医学工程研究所 | 一种基于磁声耦合效应的无创脑深部精准复合场刺激装置 |
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CN1224367A (zh) * | 1996-04-26 | 1999-07-28 | 乌尔姆大学生物医学工程研究中心 | 聚焦的磁神经刺激及检测的方法和设备 |
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- 1994-03-10 EP EP94103719A patent/EP0617982A1/de not_active Withdrawn
- 1994-03-10 DE DE4408110A patent/DE4408110A1/de not_active Withdrawn
- 1994-03-11 US US08/212,035 patent/US5476438A/en not_active Expired - Fee Related
- 1994-03-11 CN CN94102890.9A patent/CN1093937A/zh active Pending
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CN105214222A (zh) * | 2015-10-28 | 2016-01-06 | 广州丰谱信息技术有限公司 | 一种数字程控的双模超声人体理疗装置的使用方法与装置 |
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CN113101526A (zh) * | 2021-04-12 | 2021-07-13 | 中国医学科学院生物医学工程研究所 | 一种基于磁声耦合效应的无创脑深部精准复合场刺激装置 |
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Also Published As
Publication number | Publication date |
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DE4408110A1 (de) | 1994-09-15 |
EP0617982A1 (de) | 1994-10-05 |
US5476438A (en) | 1995-12-19 |
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