Source: https://patents.google.com/patent/CN1956751B/en
Timestamp: 2019-12-12 08:33:42
Document Index: 393921739

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CN1956751B - Method and device for decoupling and/or desynchronizing neural brain activity - Google Patents
Method and device for decoupling and/or desynchronizing neural brain activity Download PDF
CN1956751B
CN1956751B CN 200580016785 CN200580016785A CN1956751B CN 1956751 B CN1956751 B CN 1956751B CN 200580016785 CN200580016785 CN 200580016785 CN 200580016785 A CN200580016785 A CN 200580016785A CN 1956751 B CN1956751 B CN 1956751B
neuron population
CN 200580016785
CN1956751A (en
克里斯蒂安·豪普特曼
奥列克山大·波波维奇
彼得·塔斯
瓦莱里·克拉奇科夫斯基
于利奇研究中心有限公司
2004-05-27 Priority to DE102004025945A priority Critical patent/DE102004025945A1/en
2004-05-27 Priority to DE102004025945.3 priority
2005-04-28 Application filed by 于利奇研究中心有限公司 filed Critical 于利奇研究中心有限公司
2005-04-28 Priority to PCT/DE2005/000780 priority patent/WO2005115537A1/en
2007-05-02 Publication of CN1956751A publication Critical patent/CN1956751A/en
2012-08-22 Publication of CN1956751B publication Critical patent/CN1956751B/en
210000004556 Brain Anatomy 0 abstract title 5
230000000638 stimulation Effects 0 abstract 7
The invention relates to a device for decoupling and/or desynchronizing neural, pathologically synchronous brain activity, in which the activities in a partial region of a brain area or a functionally associated brain area are stimulated by means of an electrode, surprisingly resulting in decoupling and desynchronization of the targeted neuron population from the patient's pathological area whilethe symptoms are suppressed. In an alternative embodiment of the inventive device, the pathologically synchronous brain activity is desynchronized, which also results in the symptoms being suppressed. The feedback stimulation signal, i.e. the measured, delayed, and processed neural activity, is used as a stimulus, whereby the stimulation signal is controlled on demand in a self-regulating manner such that the magnitude of the resulting stimulating influence on the neural population that is to be decoupled or desynchronized is automatically minimized once decoupling and/or desynchronization has been successful. The inventive device does not need to be calibrated with great effort nor do the stimulation parameters need to be regulated in order for the device to be operated successfully; however, said stimulation parameters can preferably be adjusted and optimized with the aid of an additional controller. The disclosed device comprises a stimulation electrode (2) and at least one sensor (3) which are triggered using a controller so as to cause decoupling and/or desynchronization in the local environment thereof.
用于去耦和/或去同步神经大脑活动的方法和装置 Method for decoupling and / or desynchronization of neural brain activity and means
[0001] 本发明涉及用于去耦和/或去同步神经大脑活动的装置，如权利要求I的前序所述。 [0001] The present invention relates to a device for decoupling and / or desynchronization of neural brain activity, the preamble of claim I.
[0002] 能够例如在基底神经节中具有其起源的病理性同步大脑活动，也能够在像例如运动皮质之类的跟随区域（following area)中产生同步作为驱动力。 Pathologically synchronous brain activity [0002] can have its origin in the basal ganglia, for example, it is possible to follow the image area of ​​the motor cortex or the like, for example, (following area) as a driving force generated in synchronization. 这种次级同步显著涉及生成病理性症状。 This involves generating a significant secondary synchronization pathological symptoms. 本发明涉及允许驱动病理性活动从跟随区域去耦的装置，由此意味着能够致使病理性症状大大減少。 The present invention relates to permit the drive means to follow the pathological activity from decoupling region, thereby causing means being able to significantly reduce pathological symptoms. 在进ー步的实施例中，根据本发明的装置还能够用于去同歩，亦即用于抑制有节律的集体活动，或者分别对被称作驱动群体（drivingpopulation)的病理性同步神经细胞群体的神经元的集体激发进行抑制。 In an embodiment ー feed step, the device according to the invention can also be used to the same ho, i.e. for inhibiting rhythmic group activities, or be referred to respectively drive groups of pathologic (drivingpopulation) synchronized neurons neuronal excitation of collective groups were suppressed.
[0003] 在具有例如帕金森病、特发性震颤、肌张力障碍或強迫症疾病的神经或精神疾病的患者中，神经细胞群体在例如丘脑和基底神经节的大脑规定区域中病理性活动，例如过度同歩。 [0003] having eg, dystonia patients with neurological or psychiatric disease or OCD diseases such as Parkinson's disease tremor, the neural cell population, for example, the basal ganglia, thalamus and brain pathological activity specified area, such as over the same ho. 在这种情况下，大量的神经元形成同步动作电位；涉及的神经元在同步地过度激发。 In this case, a large number of neurons form a synchronized action potentials; involved in the excessive neuronal excitation synchronization. 与此相反，在健康的人中，神经元例如以不相关的方式在这些大脑区域中性质上不同地激发。 In contrast to this, in healthy humans, for example in neurons uncorrelated manner differently excited in these brain regions properties. 病理性同步大脑活动改变了例如诸如主要运动皮质之类的大脑皮层的区域中的其他大脑区域中的神经活动。 Brain activity pathologically synchronous neural activity has changed as e.g. brain regions other regions of the cerebral cortex primary motor cortex in the class. 病理性同步活动然后将其节律强加于丘脑和基底神经节的区域中的大脑皮层区域，以致最终这些区域所控制的肌肉出现病理性活动，例如有节律的颤抖(震颤）。 Pathological synchronous activity area of ​​the cortex and the thalamus and the region of its rhythms imposed in the basal ganglia, and eventually controlled by these regions pathologic muscle activity, for example, rhythmic tremor (tremor).
[0004] 在不再能够通过药物治疗的患者中，取决于症状以及疾病是单侧还是双侧地发生，单侧或双侧地实行深度电极。 [0004] In the patient is no longer possible by drug treatment, depending on the disease and symptoms occur unilateral or bilateral, unilateral or bilateral implementation of the depth of the electrode. 在这种布置中，电缆在皮肤下从头部引导到所谓的发生器，其包含具有电池的控制装置，并且植入例如锁骨区域中的皮肤之下。 In this arrangement, the cable guided under the skin from the head to the so-called generator, comprising control means having a battery, and implanted under the skin, for example in the clavicle region. 经由深度电极实行具有例如矩形脉冲的单脉冲的闻频周期序列（具有> IOOHz频率的脉冲串）的连续刺激。 The implementation of a single pulse having a rectangular pulse, for example, the depth of the electrode via audible frequency cycle sequences (> IOOHz burst frequency) of continuous stimulation. 这种方法具有抑制目标区域中神经元激发的目的。 This method has the purpose of inhibiting the target region neuron excitation. 基于标准深度刺激的有效机理仍然尚未被充分解释。 Still it has not been fully explained effective mechanism based on standard depth stimulation. 大量的研究结果表明，标准深度刺激作用就像可逆的损害，亦即就像组织的可逆消除。 A large number of research results show that the standard depth stimulation as irreversible damage, that is just as irreversible tissue removed. 标准深度刺激抑制了目标区域和/或相关大脑区域中神经元的激发。 Standard depth stimulation suppressed the target area and / or the relevant brain regions excited neurons.
[0005] 这种形式的刺激的不利特征在干，发生器的能量消耗非常高，以致于仅仅在大约I到3年之后就必须频繁地手术替换发生器及其电池。 [0005] The disadvantage of this feature in the dry form of stimulation, the generator energy consumption is very high, so that only the operation must be frequently replaced generator and the battery after approximately I to 3 years. 甚至更加不利的是，连续的高频刺激，作为分别例如丘脑或基底神经节的大脑区域中的非生理性（不自然的）输入，能够导致在几年期间受影响的神经细胞群体适应。 Even more disadvantageously, continuous high-frequency stimulation, for example, as separate brain regions of the basal ganglia or thalamus in the non-physiological (unnatural) input during years can lead to nerve cell populations affected adaptation. 为了实现相同的刺激結果，由于这种适应，于是就有必要用更高的刺激幅度来刺激。 In order to achieve the same result of stimulation due to this adaptation, so it is necessary to use a higher stimulation amplitude stimulation. 刺激幅度越大，由于相邻区域的刺激而发生副作用的可能性就越大——诸如发音困难（语言失常）、感觉迟钝（在某些情况下是非常疼痛的感觉异常）、小脑运动失调（没有辅助就不能站稳）或精神分裂症状等。 The larger the amplitude of stimulation, stimulation zone due to the possibility of side effects adjacent the greater - such as dysphonia (language disorder), dysesthesia (in some cases is very painful paresthesia), cerebellar ataxia ( can not stand without assistance) or schizophrenia-like and so on. 患者不能容忍这些副作用。 These patients can not tolerate the side effects. 在这些情况下，治疗因此在几年之后就丧失了它的有效性。 In these cases, so after a few years the treatment loses its effectiveness.
[0006] 在像例如DE 102 11 766 Al所述的其他刺激方法中，提议在需要控制的各个目标区域中施加激励。 [0006] In other stimuli like e.g. DE 102 11 766 Al a method according to the proposed excitation applied to each target area in need of control. 这些方法和这些装置的目的，不是如标准深度刺激的情况下那样简单地抑制病理性同步激发，而是使其更接近生理性的不相关激发模式。 The purpose of these methods and these devices, such as the case of the standard depth is not as simple stimulation suppressed pathologically synchronous excitation, excitation mode is not relevant but it is closer to physiological. 通过这种手段，与标准深度刺激相比，一方面电流消耗将会減少，并且另一方面，通过需求控制的刺激将会减少输入到组织中的能量。 By this means, compared with the standard depth stimulation, the current consumption will be reduced on the one hand, and on the other hand, by controlling the stimulation will be reduced demand for energy input into the tissue.
[0007] 上述刺激方法需要使用ー个或多个深度电极，这代表了高手术工作量和并发症的高风险，像在为患者植入深度电极期间的例如可能的脑组织损伤或脑出血之类。 [0007] The stimulation process requires the use one or more depth ー electrodes, which represents a high risk and a high workload surgical complications, such as implantation in a patient such as a possible damage of brain tissue or cerebral hemorrhage during the depth of the electrode class. 然而，着眼于成功治愈患者和減少副作用，应当减少这种风险。 However, focusing on the successfully treated patients and reduce side effects, should reduce this risk.
[0008] 因此本发明的目标就是要制造用于去耦和/或去同步神经大脑活动的装置，借助于此，能够和缓地并且有效地治疗具有病理性同步大脑活动的患者。 [0008] It is therefore an object of the present invention to apparatus of decoupling and / or desynchronization of neural brain activity to be used for producing, by means of this, and can be effective in treating patients with pathologically synchronous brain activity gently. 关于这一点，对非生理性持久激励的适应应当被防止。 In this regard, incentives for non-durable physiological adaptation should be prevented. 漫长的校准过程应当被防止，并且当病理性节律活动的主要频率成分经受大的波动时，刺激也应当是成功的。 Lengthy calibration process should be prevented, and when the primary frequency component of pathological rhythmic activity when subjected to large fluctuations, stimulation should be successful. 进而，该装置应当实现持久的去耦和/或去同歩，并且过渡的刺激相关非生理性状态应当在很大程度上被避免。 Further, the device should be durable decoupling and / or to the same ho, and the transition stimulus related non-physiological state should be largely avoided. 根据本发明的装置不需要另外的需求控制，其如部分6. 3所述能够随意地添加，这就是为什么在技术上容易实行，并且在控制电子装置的复杂性方面并因而同样在电流消耗方面只要作出低的要求。 The device needs no additional control of the present invention is, as described in section 6.3 which can be optionally added, which is why technically easy to implement, and the complexity of the control and the electronic device therefore also in terms of current consumption just make low demands. 根据本发明的刺激装置打算以电流节约的方式操作，以便患者中植入的刺激器的电池较少频繁地需要手术替换。 The stimulation device according to the present invention is intended to save the current operation mode, so that the patient in the implanted stimulator cells requires less frequent replacement surgery. 由于优选地只有一个电极的植入是必要的，并且由于这个电极在跟随的并因而可能更加容易接近的大脑区域中植入，像例如运动皮质区域中的外皮质电极之类，所以与深度大脑刺激的上述方法相比，根据本发明的装置代表了显著的进步。 Since preferably only one implant electrode is necessary, and for this electrode is easy to follow and thus may be more brain regions close to the implant, as for example in the motor cortex region of the outer cortical electrodes and the like, so that the depth of the brain the method of stimulation as compared with the above-described apparatus according to the invention represents a significant advance. 这是因为大脑刺激不需要深度电极——特别是在根据本发明的装置的特定实施例中，所以没有由于对动脉的伤害而在外科手术进行时发生出血的风险。 This is because the depth of the electrode need not stimulate the brain - in particular, the risk of bleeding does not occur due to damage to the artery surgery is performed in accordance with a particular embodiment of the device according to the present invention in embodiments.
[0009] 在权利要求I前序的基础上，通过权利要求I的特征部分中限定的特征，根据本发明实现了目的。 [0009] On the basis of the preamble of the claim I, by the features of claim I of the features defined, it achieves the object of the present invention. 通过使用将要去耦和/或将要去同步的神经元群体的测量过和处理过的活动作为反馈刺激信号，见部分3，令人惊异地实现了目的，其在于，神经元以这样的方式借助于电极用反馈刺激信号通过刺激处于它们的活动受影响的每种情况：将要从驱动病理性神经元群体去耦的神经元群体的完全去耦和/或去同步令人惊异地发生，作为其结果，在患者中令人惊异地抑制了症状。 By using the decoupled and / or measuring neuron population to be desynchronized activity over and treated as a feedback stimulation signal, see Section 3, surprisingly achieves the object, which is that the neurons in such a manner by means of a feedback stimulation signal to the electrode by stimulating their activity is affected in each case: from the driving pathological neuron population decoupled neuron population complete decoupling and / or desynchronization occurs surprisingly, as As a result, patients with symptoms surprisingly restrained. 在如部分8所述的根据本发明的装置的进ー步的实施例中，该装置同样能够用于例如去同步驱动神经元群体。 As to the example of the neuron population synchronous drive section 8 into ー further embodiment of the device according to the invention, the device can likewise be used. 在这个实施例中，驱动神经元群体的测量过和处理过的神经活动经由刺激电极作为反馈刺激信号施加，以便驱动神经元群体用反馈刺激信号的直接或间接刺激发生。 In this embodiment, the driving neuron population measured and processed through the neural activity through the stimulation electrode as a feedback stimulation signal is applied to drive the neuron population stimulated by a feedback signal directly or indirectly irritation occurs. 通过这种手段，以这样的方式影响了将要去同步的神经元群体：完全的去同步令人惊异地发生，作为其结果，抑制了疾病相关的症状。 By this means, in such a way affect the neuron population to be desynchronized: complete desynchronization surprisingly occurs as a result of inhibition of the symptoms associated with the disease. 为了这个目的，根据本发明的装置包含控制系统4，其接收传感器3的測量信号，并且从这个信号生成刺激信号，而且将其作为刺激施加到电极2。 For this purpose, the device according to the present invention comprises a control system 4, which receives the sensor measurement signal 3 and generates a stimulation signal from the signal, and which is applied to the electrode 2 as the stimulus.
[0010] 根据本发明的装置以电流节约的方式操作，所以患者中植入的电池较少频繁地需 [0010] The device according to the present invention in a current-saving manner of operation, so patients implanted battery needs less frequent
要替换。 To replace.
[0011] 根据本发明的装置使借助于去耦刺激在外科手术进行时实现的效果能够用于为电极选择最适当的目标点。 [0011] The device according to the present invention allows the effect of the aid in the decoupling of stimulation achieved intraoperatively electrode can be used to select the most suitable target point. 当使用如电极2那样的深度大脑电极时，在电极的植入期间，在解剖上预先计算好的目标点的区域中用根据本发明的装置以毫米步长首先执行反馈信号的测试刺激和/或导出。 When a deep brain electrode, such as 2, during implantation of the electrode, using precalculated target point on the anatomical region of the device according to the invention is performed first step in millimeters of the feedback signal and the test stimulus / or exported. 能够实现最好治疗效果的目标点被选择作为用于永久植入的目标点。 The best therapeutic effect can be achieved the target point is selected as a target point for permanent implantation.
[0012] 除了展示具有相对固定频率的频繁持久的病理性同步活动的上述疾病之外，也能够治疗其中病理性同步活动仅间歇地发生（短时间发生）的疾病。 [0012] In addition to the diseases showing pathological frequently have a relatively fixed frequency of synchronous activity lasting, it is possible to treat diseases in which pathologically synchronous activity occurs only intermittently (short incurred). 主要的指标是不再能够通过药物治疗的癫痫的治疗。 The main indicator is the treatment of epilepsy can no longer be treated by medication. 根据本发明的装置能够实现例如帕金森病、特发性震颤、肌张力障碍、癫痫、抑郁和強迫症疾病的症状的抑制。 The present invention is capable of inhibiting the symptoms of Parkinson's disease, for example, essential tremor, dystonia, epilepsy, depression and obsessive-compulsive disorder according to the disease.
[0013] 在从属权利要求中限定了本发明的有益进步。 [0013] The present invention defines a useful progress in the dependent claims.
[0014] 附图显示了本发明的示范性实施例。 [0014] The drawings show an exemplary embodiment of the present invention.
[0015] 图I显示了根据本发明的装置。 [0015] Figure I shows a device according to the invention.
[0016] 图2显示了用如部分8. I中的例子I所述的刺激的刺激去耦效果。 [0016] Figure 2 shows stimulation with stimulation as described in Part I of Example I 8. The said decoupling effect. 为了显示，在图2a到2d中，耦合在4秒钟时接通，刺激在7. 5秒钟时开始。 In order to show, in FIGS. 2a to 2d, 4 seconds when the coupling is turned on, when the stimulation begins 7.5 seconds.
[0017] 图2a :未耦合状态期间、耦合期间和刺激期间将要去耦的神经元群体的经由传感器3测量的神经活动的随时间变化。 [0017] Figure 2a: during the uncoupled state, the time measuring sensor 3 via the neural activity of the neuron population to be decoupled change during coupling and during stimulation.
[0018]图2b :未耦合状态期间、耦合期间和刺激期间将要去耦的神经元群体的激发模式的随时间变化。 [0018] Figure 2b: during the uncoupled state, the mode going excitation neuron population coupled with the time period during coupling and irritation.
[0019] 图2c :刺激间隔期间的将要去耦的神经元群体的同步范围的随时间变化。 [0019] FIG. 2c: stimulation interval will be in range of the neuron population to be decoupled change over time. 小的值对应于小的同步，而大的值则对应于强同步。 Small value corresponding to the small synchronization, and a large value is corresponding to the strong synchronization.
[0020] 图2d :刺激对将要去耦的神经元群体的合成影响、亦即耦合与刺激影响之和的随时间变化。 [0020] FIG. 2d: Synthesis stimulation effects on neuron population to be decoupled, that is coupled to the stimulation of an impact, and change over time.
[0021] 图2e :耦合之前（左）、耦合期间（中）和刺激接通（右）时的激发频率分布。 Coupling excitation frequency distribution before (left), the period (in) is coupled and turns stimulation (right) when: [0021] FIG. 2e.
[0022] 图3显示了用如部分8. I中的例子2所述的刺激激励的刺激去耦效果。 [0022] Figure 3 shows stimulation with a stimulation excitation as the second example in section 8. I decoupling effect. 为了显示，在图3a到3d中，f禹合在4秒钟时接通，刺激在7. 5秒钟时开始。 In order to display, in Figure 3a to 3d, f and Yu 4 seconds when turned on, stimulation is started when 7.5 seconds.
[0023] 图3a :未耦合状态期间、耦合期间和刺激期间将要去耦的神经元群体的经由传感器3测量的神经活动的随时间变化。 [0023] Figure 3a: during the uncoupled state, the time measuring sensor 3 via the neural activity of the neuron population to be decoupled change during coupling and during stimulation.
[0024]图3b :未耦合状态期间、耦合期间和刺激期间将要去耦的神经元群体的激发模式的随时间变化。 [0024] Figure 3b: during the uncoupled state, the mode going excitation neuron population coupled with the time period during coupling and irritation.
[0025] 图3c :将要去耦的神经元群体的同步范围的随时间变化。 [0025] FIG. 3c: the pull-in range of the neuron population to be decoupled change over time. 小的值对应于小的同步，而大的值则对应于强同歩。 Small value corresponding to the small synchronization, and corresponds to a large value with a strong ho.
[0026] 图3d :刺激对将要去耦的神经元群体的合成影响、亦即耦合与刺激影响之和的随时间变化。 [0026] FIG. 3d: Synthesis of stimulation effects on neuron population to be decoupled, that is coupled to the stimulation of an impact, and change over time.
[0027] 图3e :耦合之前（左）、耦合期间（中）和刺激接通（右）时的激发频率分布。 Coupling excitation frequency distribution before (left), the period (in) is coupled and turns stimulation (right) when: [0027] FIG. 3e.
[0028] 图4 :驱动的病理性同步神经元群体I和将要去耦的被驱动神经元群体2之间的率禹合的示意图。 [0028] FIG. 4: Driven pathologically synchronous neuron population to be decoupled and I are driven neuron population rates between 2 and Yu FIG. 例如，神经元群体2表示皮质运动前区和/或运动皮质。 E.g., neuronal populations. 2 shows a front motor cortex and / or motor cortex.
[0029] 在图2a_d和3a_d中，横坐标指示以秒为単位的时间轴，而沿着纵坐标，则测量的神经活动（图2a、3a)或激发模式（图2b、3b)或同步范围（图2c、3c)或耦合与刺激影响之和（图2d、3d)处于以任意单位绘制的每个情況。 [0029] In FIG 2a_d and 3a_d, the abscissa indicates a time axis in seconds. Unit, and the neural activity (FIG. 2a, 3a) along the ordinate, the measured or excitation mode (FIG. 2b, 3b) or synchronous range (FIG. 2c, 3c) stimulation on or coupled with the sum (FIG. 2d, 3d) is in each case plotted in arbitrary units. 经由传感器3测量的神经活动（图2a、3a)用作用于生成刺激激励的基础。 Via the neural activity measured by the sensor 3 (FIG. 2a, 3a) as a basis for generating a stimulation stimulus. 在图2e和3e中，横坐标指示频率，而纵坐标则指示具有对应频率的神经元的相对数。 In FIGS. 2e and 3e, the abscissa indicates the frequency, and the ordinate the relative number of neurons having a corresponding frequency is indicated. [0030] 根据图I的装置包含隔离放大器1，其连接到电极2和用于检测生理測量信号的至少ー个传感器3。 [0030] 1, which is connected to the electrodes of the apparatus according to FIG. I and 2 comprises an isolation amplifier for detecting physiological measurement signals ー least three sensors. 使用的电极2能够例如是外皮质电极或大脑电扱。 Electrode 2 can be used, for example, electrically or cerebral cortex of electrode Xi. 隔离放大器还连接到用于信号处理和控制的単元4，其连接到用于刺激的光发送器5。 Isolation amplifier is also connected to a signal processing and control unit 4 of radiolabeling, which is connected to the optical transmitter 5 for stimulation. 光发送器5经由光波导管6连接到光接收器7，其连接到用于信号生成的刺激器単元8。 5 optical transmitter via the optical waveguide 6 is connected to the optical receiver 7, which is connected to a signal generated by the stimulator unit 8 radiolabeling. 用于信号生成的刺激器単元8连接到电极2。 Generating a signal for radiolabeling stimulator unit 8 connected to the electrode 2. 在电极2进入隔离放大器I的输入区域，设置继电器9或晶体管。 The input region of the electrode into the isolation amplifier I 2 is provided a relay or a transistor 9. 単元4经由线10连接到遥测发送器11，其连接到遥测接收器12，所述遥测接收器12位于将要植入的装置外面，并且连接到用于显示、处理和存储数据的装置13。 Radiolabeling unit 4 is connected via line 10 to a telemetry transmitter 11, which is connected to a telemetry receiver 12, the telemetry receiver 12 located outside the apparatus to be implanted, and is connected to a display device 13 processing and storing data. 使用的传感器3能够例如是外皮质电极、大脑电极或外围电极。 3 can be used, for example, the sensor outer electrode cortex, brain electrodes or peripheral electrodes.
[0031] 电极2能够是专家已知的并且适合于根据本发明的应用的任何电极。 [0031] The electrode 2 is known to the expert and can be adapted to any application of the electrode according to the invention. 因此，在本发明的更广泛的意义上，电极是能够根据本发明施加激励的物体。 Thus, in a broader sense of the present invention, the object can be excited electrode is applied in accordance with the present invention.
[0032] 电极2例如是至少两根导线，为了刺激起见向其末端施加电位差。 [0032] The electrode 2, for example, at least two conductors, a potential difference is applied in order to stimulate sake end thereto. 它能够是宏或微电扱。 It can be a macro or micro-electrical Qi. 作为选择，电极2也能够是单根导线。 Alternatively, the electrode 2 can be a single wire. 在这种情况下，为了刺激起见，在单根导线和发生器外壳的金属部分之间施加电位差。 In this case, in order to stimulate sake, the metal portion between the single wire and a potential difference is applied to the generator housing. 另外，但不是強制性地，能够经由电极2测量电位差以记录神经活动。 Additionally, but not mandatory, the electrode 2 can be measured through a potential difference to record the nerve activity. 在进ー步的实施例中，电极2还能够由多于两个的单根导线组成，其能够既用于确定大脑中的測量信号又用于刺激。 In an embodiment ー feed step, the electrode 2 can also be made of more than two single wire composition which can be used both for determining a measurement signal and for stimulating the brain.
[0033] 在电极2包含多于两根导线的情况下，这些导线中的至少ー根也能够充当传感器3，以便在这种情况下，存在其中电极2和传感器3被组合在单个部件中的实施例。 [0033] In the case where the electrode 2 comprises more than two wires, these wires at least ー can also serve as the root of the sensor 3, so that in this case, the presence of which the electrode 2 and the sensor 3 are combined in a single component of Example. 电极2的导线能够具有不同的长度，以便它们能够刺入不同的大脑深度。 Electrode wire 2 can have different lengths, so that they are capable of penetrating different brain depths. 如果电极2由n根导线组成，其中n是大于2的整数，则能够经由至少ー对导线实现刺激，形成对的导线的任何再组合都是可能的。 If the electrode wires 2 made of n, where n is an integer greater than 2, it is possible to achieve ー stimulation via the pair of wires at least, re-formation of any combination of wires are possible. 也能够在n根导线中的一根和发生器外壳的金属部分之间执行刺激。 Stimulation can be performed between the metallic portion of the n conductors and of a generator housing. 除了这个部件之外，没有在构造上与电极2组合的传感器3也能够另外存在。 In addition to this member, there is no electrode 2 and the sensor 3 can be combined in configuration additionally present.
[0034] 经由例子并且说明性地，借助于传感器在第一步骤中通过根据本发明的装置測量神经活动。 [0034] Illustratively via examples and by means of measuring the neural activity sensor apparatus according to the invention by in a first step. 在第二步骤中，通过测量信号的进ー步处理，例如，通过在时间方面延迟神经活动，并且可能地通过将其滤波和/或放大，生成刺激信号。 In a second step by further processing the measurement signal into ー, e.g., by delaying the neural activity in terms of time, and possibly by their filtering and / or amplifying the signal generated stimulation. 从这种刺激信号中生成的刺激激励然后用于经由植入电极的第三操作步骤中的刺激。 Such stimulation signal generated from the stimulation excitation is then used to stimulate the third operation step via implanted electrodes. 作为这种刺激的后果，在刺激的组织中发生病理性活动的去耦和/或去同步。 As a consequence of this stimulation, decoupling pathologic activity in the stimulation of tissue and / or desynchronized. 在部分I中解释了根据本发明的装置操作的细节。 It explains details of operation of the device according to the present invention in Part I above.
[0035] 如部分6所述，能够在激励应用的时间控制的各种实施例中实行根据本发明的装置。 [0035] The said portion 6, the implementation of the various embodiments can be controlled at the time of application of the excitation device according to the embodiment of the invention. 激励应用的时间控制的变体是持久的、重复的和需求控制的激励应用。 Energizing time control applications variant is persistent, repetitive stimulus application and control requirements.
[0036] 根据本发明的持久激励应用是根据本发明的装置的简单实施例，其操作而没有另外的需求控制，并且如部分6. I所述持久地施加激励。 [0036] The persistent stimulus application according to the present invention is a simple embodiment of the device according to the present invention, its operation without additional control requirements, and as applied to the excitation portion 6. I permanently. 持久激励应用因而就表示了根据本发明的装置的容易植入的实施例。 Thus persistent stimulus application according to the embodiment represented readily implantable device according to the present invention. 与此同吋，以少的能量输入到将要去耦的群体或将要去同步的群体中的方式，如部分5所述，由于根据本发明的自调节的需求控制，发生了持久刺激的良好去耦和/或去同步效果。 At the same inch, with less energy input to be decoupled group or population to be desynchronized manner as described in Section 5, since the self-regulating demand control of the present invention, a good place to persistent stimulation decoupling and / or desynchronization effect.
[0037] 在根据本发明的重复激励应用中，根据本发明的装置具有以这样的方式编程的控制系统：它仅在特定的时间间隔期间向电极2施加刺激激励。 [0037] In the repeated application of the excitation according to the present invention, the device according to the invention has such a manner programmed control system: applying a stimulus to the electrode 2 during its excitation only in a specific time interval. 在这些时间间隔之外没有刺激。 No stimulation outside these time intervals. 因此以这样的方式编程控制单元4 :在部分6. 2中描述的重复刺激的实施例中，在控制単元4所确定的时刻，例如周期性地ー个接ー个地，以控制単元4所计算的持续时间生成刺激信号，并且将其递送到电极2。 Thus in such a manner that programmed control unit 4: Example repetitive stimulation described in section 6.2 in the control radiolabeling cell time is four determined, for example, periodically ー a ground ー a manner to control the radiolabeling element 4 generating a calculated duration stimulation signal, and delivers it to the electrode 2. 如持久激励应用的情况下那样，根据部分5的刺激信号的自调节的需求控制也在重复激励应用中发生。 The persistent stimulus application case above, according to the needs of self-regulating stimulation signal control section 5 are repeated excitation generation applications. [0038] 在根据本发明的需求控制的激励应用中，根据本发明的装置具有如部分6. 3所述的另外的需求控制。 [0038] In accordance with the needs of the application control excitation of the present invention having additional requirements as described in Section 6.3 of the control apparatus according to the invention. 为了这个目的，根据本发明的装置优选地装备有用于检测电极2的信号中和/或传感器3中和/或处理的神经活动中的病理性特征的发生和/或实例的装置。 For this purpose, the signal detecting electrode 2 and / or devices and / or examples of rational features occurring disease and / or neural activity in the process according to the sensor apparatus 3 of the present invention is preferably equipped for. 取决于病理性特征的发生和实例，刺激信号被递送到部分6. 3中描述的需求控制的激励应用的实施例中的电极2，以便实现脑组织的刺激。 Depending on the occurrence of pathological features and examples, the stimulation signal is delivered to the embodiment of the excitation requirements of the application described in section 6.3 of the control electrode 2 in order to achieve stimulation of the brain tissue. 通过这种手段，神经元群体中的病理性神经活动被去耦和/或去同步，并因而更加接近自然的生理状态。 By this means, the pathological neural activity of the neuron population to be decoupled and / or to synchronize, and thus closer to the natural physiological state. 病理性活动和健康活动不同在于其模式和/或其幅度和/或其频率内容和/或其随时间变化的特性变化。 Its mode and / or amplitude and / or frequency content and / or a characteristic change in different pathological activity and health activity over time. 用于检测病理性模式的装置是计算机，其处理电极2和/或传感器3的測量信号，并且将它们与计算机中存储的数据相比较。 Means for detecting a pathological model is a computer that processes and / or measuring signals of the sensor electrode 2 of 3, and comparing them with the data stored in the computer. 计算机具有存储数据的数据介质。 A computer having a data medium for storing data. 这些能够用作根据部分6和7的校准和/或控制的部分。 These can be used as part of the calibration 6 and 7 and / or in accordance with the control section. 控制单元4能够包含例如具有可比较的计算能力的芯片或另一个电子装置。 The control unit 4 can comprise an electronic device may be a chip or other comparable computing power for example.
[0039] 以这样的方式编程控制単元4 :在部分6. 3中描述的需求控制的激励应用的实施例中，以控制単元4所预定的刺激间隔生成激励并将其递送到电极2。 [0039] In such a manner a control program unit 4 radiolabeling: Example stimulus application requirements described in section 6.3 in the control to control a predetermined radiolabeling element 4 generates stimulation interval and is delivered to the excitation electrode 2. 总之，与根据本发明的装置的各个过程有关的全部參数，其用于激励的类型和強度，它们的时间延迟，以及涉及电极相关应用的信息，还有有关用于需求控制的操作并由传感器3确定的测量值，或者从其中导出的參数，都将被存储。 In summary, with all the parameters in accordance with various process apparatus relating to the present invention, the type and intensity for excitation, their time delay, and the information relates to an electrode related applications, there is demand for the relevant operation controlled by the 3 determined measurement of the sensor, or from which the derived parameters will be stored.
[0040] 控制单元4优选地以以下方式控制电极2 :控制单元4将控制数据前转到用于刺激的光发送器5，其经由光波导管6驱动光接收器7。 [0040] Preferably, the control unit 4 control electrode 2 in the following manner: the control unit 4 before the control data to the optical transmitter 5 for stimulation that drives the light receiver 7 via the optical waveguide 6. 控制信号进入光接收器7的光耦合导致控制单元4和电极2的DC隔离。 A control signal enters the light receiving optical coupler 7 causes the DC isolation control unit 4 and the electrode 2. 这就意味着防止了干扰信号从用于信号处理和控制的单元4注入到电极2中。 This means that prevents interference signals from the signal processing and control unit for injecting into the electrode 24. 将要考虑的光接收器7例如是光电元件（photocell)。 To be considered in the light receiver 7 for example a photovoltaic element (photocell). 光接收器7将经由用于刺激的光发送器5输入的信号前转到刺激器単元8。 7 before the optical receiver signal inputted via the optical transmitter for stimulation 5 to 8 membered stimulator radiolabeling. 然后经由刺激器単元8将选择的刺激经由电极2前转到大脑中的目标区域。 Then radiolabeling stimulator unit 8 via the selected target region to stimulate the brain via the electrodes 2 before. 在也经由电极2进行测量的情况下，也从用于刺激的光发送器5经由光接收器7驱动继电器9，这防止了干扰信号的注入。 It was also measured in the case 2 via the electrodes, also driven from the optical transmitter 5 for stimulation via the relay optical receiver 7 9, which prevents the interference signal injection. 继电器9或晶体管确保了紧接着在没有隔离放大器的每个激励被过度驱动之后，能够再次測量神经活动。 9 ensures that the relay or the transistor immediately after each excitation of the isolation amplifier is not overdriven, neural activity can be measured again. DC隔离没有強制性地必须通过控制信号中的光耦合再现，代替地，能够使用其他可替选的控制系统。 DC isolation is not necessarily have to be reproduced by an optical coupling control signals, instead, possible to use other alternative control system. 这些能够例如是例如超声波范围内的声波链路。 These links can be, for example, such as sound waves in the ultrasonic range. 例如通过使用适当的模拟或数字滤波器，也能够实现抗干扰控制。 For example, by using an appropriate analog or digital filters, interference control can be realized.
[0041] 进而，根据本发明的装置优选地经由遥测接收器12连接到用于显示和处理测量和/或刺激信号并且用于保存数据的装置13。 [0041] Further, the device according to the invention is preferably connected via the telemetry receiver 12 for processing and displaying the measurement and / or stimulation signals and means 13 for holding data. 在这种布置中，単元13能够具有用于下述数据分析的方法。 In this arrangement, the element 13 can have a radiolabeling method described below for data analysis.
[0042] 进而，根据本发明的装置能够经由遥测接收器13连接到另外的參考数据库，以便监视例如装置的正确操作，并且可能地通过修改參数使部分7. 2中描述的控制机制更加有效。 [0042] Further, the device according to the invention can be connected to the telemetry receiver 13 via the reference database to another, for example in order to monitor the correct operation of the device, and possibly cause control mechanism described in section 7.2 more efficient by modifying the parameters .
[0043] 在部分I中，详细地解释了刺激的机理。 [0043] In Part I, explained in detail the mechanism of stimulation. 最重要术语的定义能够在部分2中找到。 Define the most important terms can be found in section 2. 从神经活动的测量经由它们的处理一直到生成刺激信号的操作步骤在部分3中解释。 From the measured neural activity through their processing through the generation of stimulation signals steps explained in section 3. 电极和传感器的空间布置是部分4的主題。 Spatial arrangement and the sensor electrode portion 4 are the subject. 部分5处理刺激信号的自调节的需求控制。 Processing section 5 adjusting the stimulation signal from the demand control. 在部分6和7中，描述了激励应用的控制以及刺激參数的校准和适应。 In section 6 and 7, a control and calibration of stimulus application and adaptation of the stimulation parameters. 在部分8中，解释了装置的例子和其他可能的使用和实施例。 In section 8, an example to explain the device and other possible uses and embodiments. 在部分9中列出了根据本发明的装置的优点。 Lists the advantages of the device according to the invention in section 9.
[0044] 刺激的机理[0045] 根据本发明的方法和装置能够用于将被驱动的神经元群体从驱动的神经元群体去耦。 [0044] The mechanism of stimulation [0045] The method and apparatus of the present invention can be used to be driven neuron population from the driving neuron population decoupling. 驱动的神经元群体也能够被去同歩。 Driven neuron population can also be to the same ho. 在图4中显示了这种关系。 This relationship is shown in FIG. 4.
[0046] 这是通过借助于电极施加激励作出的，所述激励通过以下生成：測量神经活动，并且在可能存在的、优选地还包括时间延迟的任何处理步骤之后，将其转换成刺激信号并进一步转换成刺激激励，并且将其施加以便去耦和/或去同步令人惊异地发生。 [0046] This is made in the excitation, the excitation generated by applying an electrode by means: After the measurement of neural activity, and may be present, preferably further comprising the step of processing any time delay, converts it into a stimulation signal and further converted into stimulation stimulus, and applies it to decouple and / or desynchronization surprisingly occurs. 如部分3. I所述，在去耦过程中刺激被驱动的神经单元群体2(图4)。 As described in Section 3. I, to stimulate the nerve cell group 2 is driven (FIG. 4) in the decoupling process. 在去同步过程中，刺激驱动的神经元群体I。 In the de-synchronization process, the stimulus-driven neuron population I. 使用根据本发明的装置和根据本发明的刺激方法，将要去耦的神经单元群体被直接带入到去耦和去同步的状态中，或者将要去同步的群体被去同步。 And using the decoupling desynchronized state, or population to be desynchronized is desynchronized apparatus according to the present invention and the stimulation method of the present invention, the neural cell population to be decoupled is directly brought. 希望的状态，換言之即完全的去耦和/或去同歩，典型地在神经活动的几个周期期间、常常在少于ー个周期内发生。 Desired state, in other words, complete decoupling and / or to the same ho, typically over several periods of neural activity, often less than ー occurs in cycles. 持久或重复刺激的必要性典型地存在，因为将要去耦和/或将要去同步的神经单元群体，根据经验，在已断开刺激之后，由于生病和/或由于耦合，会再次再同歩。 Necessity of a persistent or repetitive stimulation typically exists as to be decoupled and / or neural cell population going synchronization, based on experience, after stimulation has been disconnected, due to illness, and / or due to the coupling, will then again with ho. 由于根据本发明，刺激直接与神经活动相关联，所以对将要去耦或将要去同步的神经元群体的合成刺激影响、亦即耦合与刺激之和的幅度，在成功去耦和/或去同步之后被自动最小化。 Since the present invention, is directly associated with stimulation of neuronal activity, the effect on the stimulation of the synthesis to be decoupled or the neuron population to be desynchronized, i.e. coupled and the stimulation amplitude, successful decoupling and / or desynchronization in after it is automatically minimized. 由于下述事实使这成为可能：反馈刺激信号、換言之即处理的神经活动用作刺激，亦即同步并因而耦合的范围，持久地控制刺激信号的強度和形式。 Due to the fact it makes this possible: the neural stimulation activity as a feedback stimulation signal, in other words, processing, i.e. synchronized and thus the range of the coupling, controlling the intensity and lasting form of the stimulation signal. 施加的刺激信号补偿了外部耦合和/或内部同步的力，所以对将要去耦或将要去同步的神经元群体的合成刺激影响的幅度被最小化，并且它们的神经活动更加接近自然的生理状态。 Stimulation signal is applied to compensate for external coupling and / or internal synchronization force, so that the amplitude of stimulation on the neuron population to be decoupled or to be desynchronized synthesis is minimized, and their neural activity closer to the physiological state of naturally . 这个过程对大范围的可修改的刺激參数起作用，像例如刺激周期T、时间延迟和强度之类，并不需要任何精心设计的校准，并且具有大的容错。 This process may be modified in a wide range of stimulation parameters of functions, like for example the stimulation period T, the intensity and time delay class, does not need any elaborate calibration, and has a large error tolerance. 进而，输入到将要去耦或将要去同步的组织中的能量，由于神经活动和刺激模式之间的直接关系而被最小化，这允许预期更小的副作用。 Furthermore, the energy input into the tissue to be decoupled or to be desynchronized is due to the direct relationship between activity and nerve stimulus pattern is minimized, which allows less side effects is expected.
[0047] 在随后的文本中，将经由例子解释根据本发明的装置及其操作。 [0047] In the text which follows, by way of example to explain the apparatus according to the present invention and its operation.
[0048] 根据本发明的装置和控制系统装备有这样的装置，其能够执行根据本发明的治疗方法的全部步骤。 [0048] Such devices have a control system and apparatus according to the present invention is equipped, capable of performing all of the steps of the method of treatment according to the present invention. 使用披露的方法步骤，用于执行方法步骤的装置也将被隐含地披露。 The step of using the disclosed methods, apparatus for performing the method steps will be disclosed implicitly. 方法步骤因而与此同时表示了功能化的装置特征。 Thus at the same time it represents the method step functionalized device features.
[0049] 根据本发明，电极被引入到大脑区域中或者——在外皮质电极的情况下——附着到大脑区域。 [0049] According to the present invention, the electrode is introduced into the area of ​​the brain, or - in the case of the outer cortical electrodes - is attached to the brain region. 这种大脑区域优选地以这样的方式选择：它直接或间接地连接到ー个或多个大脑区域，或者直接属于这些区域中之一，所述区域负责形成疾病模式或者由病理性活动驱动。 Such areas of the brain are preferably selected in such a way: it is directly or indirectly connected to one or more brain regions ー, or directly belonging to one of these regions, the region responsible for the formation of patterns of disease or pathological event driven.
[0050] 关于这一点，电极在其环境中递送电信号，所述电信号在其环境中或经由神经纤维束带离的另ー个区域中直接产生去耦和/或去同歩。 [0050] In this regard, the electrodes electric signals delivered in its environment, in which the electrical signal from the environment or nerve fibers via another band regions directly generated ー decoupling and / or to the same ho. 为了产生去耦和/或去同步，測量并处理的、优选地时间延迟的神经活动用作刺激信号，见部分3。 To produce decoupling and / or desynchronization, and the measurement process, preferably as a time delay neural activity stimulation signal, see section 3. 根据本发明的装置因此具有以这样的方式驱动电极2的控制系统：它在其比较接近的环境中和/或在通过经由纤维束来前转刺激的另ー个大脑区域中实现去耦和/或去同歩。 Thus having such a manner that the drive electrode control system 2 of the apparatus according to the invention: it is in its close environment, and / or to achieve more brain regions by transfection stimulated via the front fiber bundle to another ー decoupling and / or go to the same ho. 根据本发明，电极用刺激驱动，所述刺激是从具有优选地T/2整数倍的时间延迟的测量并处理的神经活动中形成的。 According to the present invention, a drive electrode stimulation, the stimulus is formed from a / 2 and nerve activity measurement processing an integral multiple of a time delay T, having preferably. T是刺激周期，并且如下所述，基本上近似于驱动或被驱动的神经元群体的有节律神经活动的周期。 T is the stimulation period, and as described below, the neural activity has a circadian rhythm substantially similar to the driving or driven neuron population. 如果刺激电极2没有位于将要去耦和将要去同步的区域中，则当驱动这样的电极2时，必须考虑刺激位置和它影响的神经元群体的位置之间的传播时间。 If the stimulation electrode 2 is not located in the region to be decoupled and to be desynchronized, then when this driving electrodes 2, must take into account the propagation time between the stimulus location and the location of the neuron population affected by it. 这在部分7. 3中描述。 This is described in section 7.3. 令人惊异地，这种刺激导致与病理性症状的抑制相关联的将要去耦的整个神经元群体的去耦和去同步以及/或者将要去同步的神经元群体的去同歩。 Surprisingly, this stimulation results in pathological conditions associated with the inhibition of disease decoupling decoupled entire population of neurons and desynchronized and / or go to the same ho neuron population to be desynchronized. 如果电极2位于将要去耦和将要去同步的区域之外，则必须考虑间接刺激的效果，如部分7. 3所述。 If the electrode 2 is located to be decoupled and outside the area to be desynchronized, it must consider the effect of indirect stimulation, as described in section 7.3.
[0051] 使用新颖的方法和新颖的装置，与上述现有技术相比，以性质上不同的方法实现了抑制病理性症状的目标。 [0051] The use of the novel method and novel apparatus, as compared with the prior art, on the nature of the different methods to achieve the goal of inhibiting pathological symptoms. 代替用强刺激激励抑制病理性同步神经细胞群体的神经活动，病理性同步驱动神经细胞群体被简单地去同步，或者病理性活动所驱动的别的神经元群体从这种力中去耦和去同步，这导致病理性症状的抑制。 Instead of suppressing the excitation strong stimulation pathologically synchronous neural cell population neural activity, pathologically synchronous driving nerve cell population is simply to synchronize, or pathological activity driven by the neuron population from other such force to the decoupling and synchronization, which results in inhibition of pathological symptoms. 単独神经元的生理性活动不受影响。 Physiological activity radiolabeling single neurons affected. 在这个过程期间，根据部分3. 3处理的神经活动用在激励的位置处。 During this process, the neural activity in accordance with section 3.3 treated at the position of the excitation. 去耦和/或去同步令人惊异地发生是由驱动区域中神经元之间的交互作用支持的。 Decoupling and / or desynchronization surprisingly occurs by the interaction between the support drive region neurons. 这利用了负责病理性同步的作用机制。 This takes advantage of the mechanism of action responsible for the pathological synchronization. 说明性地，将要影响的系统的能量用于以最小的干预实现治疗效果。 Illustratively, affect the energy system to be used with minimal intervention achieve a therapeutic effect. 如果使用这样的刺激激励，所述刺激激励从时间延迟对应于刺激周期T 一半的整数倍的刺激信号中生成，则获得最好的結果。 If such a stimulation stimulus, the stimulus corresponding to the delay time from the excitation generating the stimulation signal to the stimulation period T of an integer multiple of a half, the best results are obtained. 刺激周期T近似于病理性活动的周期。 Stimulation period T is similar to pathological activity cycle. 然而，如果电极2递送的激励的时间延迟包含其他的时间延迟，则同样实现治疗成功。 However, if the excitation electrode 2 delivery time delay comprises a time delay of the other, to achieve the same therapeutic success. 在这样的情况下，产生例如至少部分的去耦和/或去同歩。 In such a case, for example, to produce at least a portion of the decoupling and / or to the same ho. 然而，选择的时间延迟越接近病理性活动周期一半的倍数，治疗结果会越好。 However, the selected time delay is closer to half of pathological activity cycle multiples, the better the treatment outcome.
[0052] 术语定义 [0052] Definition
[0053] 神经活动： [0053] neural activity:
[0054] 根据本发明的装置的机制描述基本上基于术语神经活动。 [0054] The mechanism described apparatus of the present invention is essentially based on the term neural activity. 将要去耦的神经元群体和/或将要去同步的神经元群体（见术语驱动和被驱动群体）的神经活动被測量、存储、并且根据部分3. 3被处理并用作反馈刺激信号，作为其结果实行根据本发明的自调节的需求控制。 The neural activity of the neuron population to be decoupled and / or a neuron population to be desynchronized (see terms drive and driven population) is measured, stored, and processed and used as feedback stimulation signal according to section 3.3, as results of the self-regulating effects control according to the present invention needs. 在随后的文本中，将要去耦的神经元群体和/或将要去同步的神经元群体的测量的神经活动被理解为这样的信号，其再现将要去耦的神经元群体和/或将要去同步的神经元群体的活动的随时间发展。 In the text which follows, to be decoupled neuron population and / or neural activity measurement of the neuron population to be desynchronized is understood as a signal which reproduces the decoupled neuron population and / or to be desynchronized over time, the development activities of the neuron population. 例如，局部场势（local fieldpotential)能够再现将要去I禹的神经元群体和/或将要去同步的神经元群体的活动的随时间发展。 For example, the local field potential (local fieldpotential) can be reproduced going Yu I neuron population over time and / or activity of the neuron population to be desynchronized development. 神经活动能够优选地在将要去耦的区域中和/或将要去同步的区域中直接測量，但是也可以测量与将要去耦的区域和/或将要去同步的区域的神经活动相关联的活动，例如别的大脑区域的活动，例如运动皮质和/或皮质运动前区的活动，或者将要由将要去耦的区域和/或将要去同步的区域控制的肌肉组的活动。 Neural activity can preferably be measured directly in the area to be decoupled and / or the area to be desynchronized, but it can also be measured with the decoupled regions and / or activities of nerve activity area associated with the desynchronized, other brain regions such as activity, e.g. premotor cortex activity and / or motor cortex, or to be decoupled from the region and / or activity of the muscle groups of the control region to be desynchronized. 在根据本发明的装置的进ー步的实施例中，神经活动能够在各种位置測量并组合，以便获得将要去耦的神经元群体和/或将要去同步的神经元群体的神经活动的充分代表性。 According to an embodiment full step into ー apparatus according to the present invention, the neural activity can be measured and combined in various positions, in order to obtain the neuron population to be decoupled and / or neural activity of the neuron population to be desynchronized representative. 与将要去耦的区域和/或将要去同步的区域的神经活动相关联的这些量在随后的文本中也将被称作神经活动并包含在这个术语中。 The region to be decoupled and / or the amount of neural activity associated with the area to be desynchronized in the text which follows will be referred to as neural activity and included in this term.
[0055]节律： [0055] rhythm:
[0056] 节律被理解为有节律的，換言之即近似周期性的神经活动，其能够作为神经细胞的病理性过度同步活动的后果而产生。 [0056] rhythm is understood to have rhythm, in other words approximately periodic neural activity, which is capable of generating neurons as pathological consequences of excessive synchronous activity. 节律能够短时间发生或者持续长时间。 Rhythm can be sustained for a long time or a short time occurrence.
[0057]周期： [0057] Cycle:
[0058] 用于根据本发明的装置的中心术语是有节律的神经活动的周期，其用作用于刺激激励应用的时间基准。 [0058] The term center of the device according to the present invention is a cycle neural activity rhythms, which is used as a time reference excitation stimulation applications. 像例如部分7. 2. I所述的刺激周期T的适应优选地具有下述效果：有节律的神经活动的周期对应于刺激周期T。 Like for example the part 7. 2. I stimulation period T is preferably adapted to have the following effects: the rhythmic neural activity period corresponding to the stimulation period T.
[0059] 驱动群体：[0060] 驱动群体被理解为这样的神经细胞群体，其生成病理性同步神经活动，或者再现从属区域的病理性同步活动。 [0059] Drive groups: [0060] The drive group is understood to be a neural cell population that generates pathologically synchronous neural activity or slave region reproducing pathological synchronous activity. 驱动群体能够将病理性同步活动前转到被驱动群体（图4)。 Group will be transferred to the drive can be driven groups (Figure 4) before the pathologically synchronous activity. 驱动神经元群体的病理性节律被产生： Driving neuron population pathological rhythm is generated:
[0061] (I)涉及基本上整体的驱动神经元群体和/或（2)以部分的驱动神经元群体和/或（3)以不同于驱动和被驱动神经元群体的第三神经元群体，其驱动驱动神经元群体。 [0061] (I) involves substantially the entire driving neuron population and / or (2) to drive neuron population portion and / or (3) different from the drive and driven neuron population of a third population of neurons its driving neuron population. 在 in
(3)的情况下，驱动神经元群体自身是被驱动神经元群体。 Case (3), the driving neuron population is itself driven neuron population. 驱动神经元群体也被称作将要去同步的群体或将要去同步的区域。 Driving neuron population to be desynchronized is also referred to as area or population to be desynchronized. 驱动神经细胞群体并不束缚于解剖界限。 Driving nerve cell population is not tied to anatomical boundaries. 代替地，它还能够被理解为由以下的组所组成的至少ー个组成部分： Instead, it can be understood by ー component of at least the group consisting of:
[0062] ——至少ー个解剖区域的至少ー个部分； [0062] - at least one anatomical region ー ー least portions;
[0063] ——至少ー个完全的解剖区域。 [0063] - at least ー fully anatomical region.
[0064] 被驱动群体： [0064] driven groups:
[0065] 被驱动群体被理解为这样的神经细胞群体，其经由驱动群体直接或间接受影响(图4)。 [0065] is driven groups is understood to be a neural cell population that receives directly or via a drive impact groups (FIG. 4). 直接影响是指经由直接连接两个群体的纤维——亦即没有别的群体插入的影响。 Via a direct impact refers to the direct connection of two groups of fibers - i.e. not affect other groups inserted. 间接影响是指经由至少ー个插入群体的影响。 Indirect influence means via ー affect at least one insert groups. 受驱动群体影响的神经细胞群体也被称作将要去耦的神经元群体或将要去耦的区域。 Nerve cell populations affected also referred to as drive groups to be decoupled or the neuron population to be decoupled region. 将要去耦的区域并不束缚于解剖界限。 The decoupled area is not tied to anatomical boundaries. 代替地，它还能够被理解为由以下的组所组成的至少ー个组成部分： Instead, it can be understood by ー component of at least the group consisting of:
[0066] ——至少ー个解剖区域的至少一部分； [0066] - at least ー least a portion of the anatomical region;
[0067] ——至少ー个完全的解剖区域。 [0067] - at least ー fully anatomical region.
[0068]丘脑下神经核-苍白球（nucleus subthalamicus-globus pallidus)外部的区域的连接，其由于疾病而充当起搏器并且能够生成病理性有节律的同步活动，能够用作驱动神经元群体的例子。 [0068] hypothalamus nucleus - globus pallidus (nucleus subthalamicus-globus pallidus) outside the connection region, which acts as a pacemaker due to disease and can generate rhythmic pathological synchronous activity, can be used as a drive neuron population example. 生成的同步活动控制大脑区域、例如运动皮质的神经活动，其在这里能够被称作被驱动群体，并且还连接到肌肉并控制它们的活动。 Generated synchronization control active region of the brain, for example, motor cortex neural activity, which is referred to herein can be driven groups, and also connected to the control muscles and their activities.
[0069] 去耦刺激： [0069] decoupling stimulation:
[0070] 去耦刺激在本发明的意义上被理解为这样的刺激，其使驱动神经元群体对被驱动神经元群体的病理性驱动效果最小化到这样的程度：它不再功能性地扮演角色——換言之即用于症状的实例。 [0070] Decoupling stimulation in the sense of this invention is understood as a stimulus, which the driving neuron population pathologic effect driving neuron population to be driven is minimized to the extent: it no longer plays a functionally role - in other words, for instance symptoms.
[0071] 目标群体： [0071] target groups:
[0072] 在随后的文本中，目标群体被理解为植入的刺激电极所直接刺激的神经细胞群体。 [0072] In the text which follows, the target population is understood as the stimulation electrode implanted directly stimulate neural cell population. 通过它里面或其附近植入的电极直接刺激目标群体。 Through its inside or near the implanted electrodes directly stimulate the target group. 直接或间接地刺激将要去耦和/或将要去同步的群体。 Directly or indirectly stimulate decoupled and / or the population to be desynchronized.
[0073] 直接刺激： [0073] Direct stimulation:
[0074] 在这种情况下，刺激电极2直接位于将要去耦的区域中或将要去同步的区域中。 [0074] In this case, the stimulation electrode 2 is located directly in the region to be decoupled or the area to be desynchronized. 这个电极2影响位于将要去耦的区域中或将要去同步的区域中的目标群体。 The electrode 2 is located in the target group will affect the region or regions to be decoupled in the desynchronized.
[0075] 间接刺激： [0075] Indirect irritation:
[0076] 在这种情况下，没有直接借助于刺激电极2刺激将要去耦的区域或将要去同步的区域。 [0076] In this case, there is no direct means of stimulation stimulate the area of ​​the electrode 2 to be decoupled or going sync region. 代替地，通过电极2刺激功能上紧密连接到将要去耦的区域或将要去同步的区域的目标群体或纤维束。 Instead, the upper electrode 2 connected by tight stimulation function to the area to be decoupled or going to the target area of ​​the fiber bundle or group synchronization. 在这个过程中，优选地经由解剖连接来带离对将要去耦的区域或将要去同步的区域的刺激影响。 In this process, preferably via anatomical connections away from the stimulation on a region to be decoupled or the area to be desynchronized. 对于间接刺激，目标区域将被作为用于目标群体和纤维束的通称引入。 For indirect stimulation, the target region will be incorporated generic term for the target groups and fiber bundles. 关于术语目标区域，功能上紧密地连接到将要去耦的区域或将要去同步的区域的神经元群体以及连接纤维束将在随后的文本中被理解，其由植入电极2直接刺激。 The term target area, the closely attached area to be decoupled to function or area of ​​the neuron population to be desynchronized and the joint fiber bundle is to be understood in the text which follows, which is by the direct stimulation of implanted electrodes 2.
[0077] 时间延迟：[0078] 根据本发明的装置将信号前转到刺激电极2，其根据部分3. 2，能够对应于较早时间的测量过并可能处理过的神经活动（=反馈刺激信号）。 [0077] Time delay: [0078] The apparatus according to the invention prior to stimulation signal electrode 2, based on 3.2 part, the measurement can correspond to an earlier time, and may be processed through the neural activity (= feedback stimulation signal). 这个时移在随后的文本中将被称作时间延迟，并且表示与刺激周期T相关联的重要刺激參数，所述刺激周期T对应于有节律的神经活动的周期。 This time shift in the subsequent text be referred to as a time delay, and represents a significant stimulation parameters associated with the stimulation period T, the period T corresponds to a period of stimulation rhythmic neural activity.
[0079] 反馈刺激信号： [0079] Feedback stimulation signal:
[0080] 反馈刺激信号或刺激信号被理解为这样的信号，其表示測量过并处理过的神经活动，并且用作用于刺激的基础。 [0080] Feedback stimulation signal or stimulation signal is understood to be a signal, which represents the measured neural activity through and processed, and used as a basis for stimulation. 例如，能够如部分3. 3所述执行处理步骤。 For example, the portion of the processing steps can be performed 3.3 As. 刺激信号由处理过的神经活动组成，并且用于刺激将要去耦的大脑区域或将要去同步的大脑区域。 Stimulation signal processed by the neural activity and is used for stimulation of the brain region to be decoupled or the brain region to be desynchronized. 执行反馈刺激信号，可能有必要通过多重处理步骤生成測量信号，所述处理步骤可能相互独立，具有不同的处理參数（具体地即不同的时间延迟），其然后例如相加和/或相乘和/或相除和/或相减和/或借助于其他的非线性函数计算，用于形成实际的刺激信号。 Performs feedback stimulation signal, it may be necessary measurement signal is generated by the multi-processing step, the processing step may be independent of each other, have different processing parameters (i.e., specifically different time delays), which then e.g. addition and / or multiplication and / or division and / or subtraction and other nonlinear function calculating / or by means of forming the actual stimulation signal. 从反馈刺激信号中，刺激激励被生成，然后借助于电极施加到目标群体。 Stimulation signal from the feedback, the stimulation excitation is generated by means of electrodes is then applied to the target group.
[0081] 合成刺激影响 [0081] Synthesis Stimulating
[0082] 对将要去耦的神经元群体或将要去同步的神经元群体的合成刺激影响被理解为向将要去耦和/或将要去同步的群体施加的外力之和。 [0082] Synthesis of stimulation on the neuron population to be decoupled or the neuron population to be desynchronized is understood as the force applied to be decoupled and / or groups and to be desynchronized. 根据部分3. 1，在根据本发明的装置的一个实施例中，借助于直接或间接刺激将被驱动神经元群体从驱动神经元群体去耦。 The part 3.1, the neuron population from the driving decoupling apparatus according to one embodiment of the present invention, will be driven by means of directly or indirectly stimulating neuronal populations. 在这种情况下，对将要去耦的群体的结果刺激影响是刺激信号和耦合到驱动群体的驱动カ之和。 In this case, the results of a population to be decoupled stimulation in stimulation signal is coupled to the drive groups and the sum driving ka. 在根据本发明的装置的另ー个实施例中，借助于该刺激来去同步将要去同步的驱动群体。 In the apparatus of the present invention ー another embodiment of the embodiment, by means of which the synchronous stimulating come going to drive the synchronous groups. 对将要去同步的群体的合成刺激影响在这里只是刺激信号。 The resultant stimulation influence desynchronized population here is only the stimulation signal pairs. 由于部分5中描述的自调节的需求控制，对将要去耦的神经元群体或将要去同步的神经元群体的合成刺激影响的幅度，在成功去耦和/或去同步之后自动最小化。 As part of the self-regulating demand control described in 5, the amplitude of stimulation will affect the synthesis of the neuron population to be decoupled or the neuron population to be desynchronized, automatically minimized after successful decoupling and / or desynchronization.
[0083] 刺激方法和激励的形成 [0083] The method of formation stimulation and motivation
[0084] 3. I去耦和去同步方法 [0084] 3. I decoupled and desynchronized method
[0085] 大脑区域中的病理性同步神经元群体由于有节律的活动而能够充当别的跟随神经元群体上的驱动カ。 Pathologically synchronous neuron population [0085] Since the activity of brain regions and can act as a rhythmic drive other grades follow on the neuronal populations. 这能够导致群体之间“驱动群体-被驱动群体”形式的交互作用体制，如图4中图解显示的那样。 This can result in "drive groups - groups is driven" system in the form of interaction between groups, illustrated in FIG. 4 as shown. 如果驱动力足够强，则被驱动神经元群体也将变得同步，这能够产生病理性症状。 If the driving force is strong enough, the driven neuron population will become synchronized, which can produce pathological symptoms. 这当被驱动群体驱动肌肉时发生，如皮质运动前区或运动皮质中的情况那样。 This occurs when driven by the drive muscle groups, as in the case before the motor cortex or motor cortex above.
[0086] 如部分I中所述，根据本发明的装置和根据本发明的刺激方法的目标是去同步病理性同步神经活动，其允许预期抑制症状。 In the [0086] The section I, the device according to the invention and the method of the present invention, the target stimulation is desynchronized pathologically synchronous neural activity, which is expected to allow the suppression of symptoms. 在去耦刺激模式的情况下，被驱动神经元群体2从驱动群体I去耦和去同步，或者，在去同步刺激模式的情况下，为了这个目的，来去同步驱动神经元群体I。 In the case where the decoupling stimulation mode 2 is driven from the driving neuron population groups decoupled and desynchronized I, or, in the case of desynchronization stimulus patterns, for this purpose, driving synchronization come neuron population I.
[0087] 在去耦刺激模式下，借助于刺激电极根据部分3. 4和4. I直接或间接地刺激被驱动神经元群体2。 [0087] In the decoupling mode stimulation, the stimulation electrode by means of stimulation of the neuron population to be driven directly or indirectly 2 partial 3.4 and 4. I. 刺激产生神经元群体从驱动神经元群体I的去耦，这导致群体2的去同 Stimulates neuron population from the driving neuron population decoupled I, which leads to the same group 2
[0088] 在去同步刺激模式下，借助于刺激电极直接或间接地刺激驱动神经元群体I。 [0088] In the stimulation of de-synchronization mode, the stimulation electrode by means of directly or indirectly stimulating the driving neuron population I. 借助于这种刺激，群体I被去同歩，以便其在群体2上的驱动カ消失。 By means of such stimulation, to be the same group I ho, so that the driving population in grades 2 disappears. 后者也被去同步，作为其结果，病理性症状被抑制。 The latter is also desynchronized as a result of pathological symptoms are suppressed. 如果群体2自身同歩，则它必须像驱动神经元群体一祥直接去同 If the 2 groups with their own ho, it must be like driving neuron population to go with a direct Cheung
[0089] 根据部分5，刺激信号的自调节的需求控制在两种上述刺激方法中发生，其中对刺激的神经元群体的合成刺激影响自动最小化。 [0089] According to section 5, the self-regulating demand stimulus control signal occurs in both of the above stimulation methods, wherein the synthetic stimulation on the neuron population stimulated automatically minimized. 根据部分2，在去耦刺激模式下对被驱动神经元群体的合成刺激影响是刺激信号与驱动群体的驱动カ之和。 The section 2, in the stimulation mode decoupling stimulation on the synthesis of the neuron population to be driven by the drive ka stimulation signal and the drive groups. 在去同步刺激方法中，对驱动神经元群体的合成刺激影响独有地为刺激信号的影响。 In the method of desynchronization stimulation, stimulation on the synthesis of the driving neuron population stimulated exclusively to affect the signal.
[0090] 在随后的文本中，经由例子、亦即去耦刺激模式描述根据本发明的装置的实施例，其中，将要去耦的神经元群体借助于直接或间接刺激从驱动神经元群体去耦。 [0090] In the text which follows, by example, i.e. the decoupling stimulation mode described embodiment of the device according to the present invention, wherein the neuron population to be decoupled by means of directly or indirectly stimulating neuron population from the driving decoupling . 根据本发明的装置的进ー步的实施例在部分8中描述。 Described in Example 8 part further into ー apparatus of the present invention. [0091] 3. 2测量神经活动 [0091] 3.2 measured neural activity
[0092] 将要去耦的区域和/或驱动区域的神经活动的随时间变化能够经由传感器3直接和/或间接地測量。 [0092] The change over time zone and / or nerve activity to be decoupled driving area 3 can be measured directly or indirectly and / or via a sensor.
[0093] 在间接测量的情况下，对受将要去耦的区域影响的肌肉组的和/或驱动区域的活动的随时间变化，和/或与将要去耦的区域和/或驱动区域相关联的神经元群体的活动的随时间的变化进行測量。 [0093] In the case of indirect measurement, change over time of and / or activity drive region muscle group Take affected to be decoupled to and / or decoupled regions and / or drive region associated over time the activity of the neuron population is measured.
[0094] 传感器3(见图I)位于大脑内和/或大脑外。 [0094] The sensor 3 (see FIG. I) is located in the brain and / or outside the brain. 在大脑内，它们安置在将要去耦的区域和/或驱动区域内和/或功能上连接到其的至少ー个其他区域内。 In the brain, they are disposed in or on the region to be decoupled and / or the drive region and / functionally connected to the at least ー other regions thereof. 在大脑外，传感器3位于连接到病理性同步神经活动的身体部位，例如像颤抖肌肉中的电极那样。 Outside the brain, located in the body part the sensor 3 is connected to the pathologically synchronous neural activity, such as an electrode as muscle tremor. 在用于信号处理的単元4中处理并存储例如肌肉活动（其也被称作神经活动，见部分2)的神经元群体的神经活动的測量信号。 Measurement signal neural activity of the neuron population radiolabeling element 4 for signal processing and storing processing such as muscle activity (which is also referred to as neural activity, see section 2) is. 測量、处理和存储能够持久地或以离散的时间间隔执行。 Measuring, processing, and storage can be permanently or at discrete time intervals. 在后者的情况下，离散测量间隔的持续时间和/或间隔由确定性和/或随机算法确定。 In the latter case, the discrete-time measurement interval duration and / or spacing is determined by the deterministic and / or stochastic algorithm.
[0095] 3. 3处理神经测量信号 [0095] 3.3 neural processing the measurement signal
[0096] 然后处理用于信号处理的単元4中存储的測量信号，以便可用作反馈刺激信号。 Element radiolabeling measurement signals stored in the [0096] then processed for signal processing, in order to be used as a feedback stimulation signal. 能够施加以下处理步骤： The following processing steps can be applied:
[0097] I.能够滤波测量的神经活动，例如能够带通滤波神经活动。 [0097] I. filtering neural activity can be measured, for example, band-pass filtering neural activity. 滤波可能是必要的，如果除了疾病相关的活动之外，例如从其他神经元群体经由传感器3測量非疾病相关的活动的话。 Filtering may be necessary, if in addition to the activities associated diseases, such as neuron population from other activities related to the measurement sensor 3 via the non-disease words. 由于疾病相关的活动典型地在与非疾病相关的活动的频率范围不同的频率范围内发生，所以在这种情况下优选地在疾病相关的频率范围内确定该活动。 Since typically occurs at different frequency ranges associated with non-disease activity associated with a frequency range of disease activity, it is preferable to determine the activity of disease in the frequency range in this case. 这例如借助于频率分析实现。 This is achieved e.g. by means of frequency analysis. 类似地，可能有必要执行小波分析和/或希耳伯特（Hilbert)变换和/或时域中的滤波。 Similarly, it may be necessary filtering wavelet analysis and / or Hilbert (in Hilbert) transformation and / or time domain is performed.
[0098] 2.如果经由若干传感器3测量将要去耦的神经元群体和/或将要去同步的神经元群体的神经活动，则能够线性和/或非线性地组合测量的神经活动。 [0098] 2. If the number of sensors via 3 measuring the neuron population to be decoupled and / or neural activity of the neuron population to be desynchronized, it is possible to linear and / or non-linear combination of the measured neural activity. 例如，测量的神经信号相互或自身相乘、相除、相加和/或相减，和/或借助于其他的非线性函数变换。 For example, nerve signal measurements multiplied by itself or each other, division, addition and / or subtraction, and / or by means of other nonlinear transformation function.
[0099] 3.在时间方面延迟测量的神经活动。 [0099] 3. The delay measured neural activity in terms of time. 用于这个目的的时间延迟在部分3. 4中定义，并且根据部分7. 3，还考虑刺激电极关于将要去耦的神经元群体的位置。 For this purpose the time delay is defined in section 3.4, and in accordance with section 7.3, the location of the stimulating electrode is also contemplated neuron population to be decoupled. 另外，根据部分7. 2. I和7. 2. 2，优选地能够在刺激期间使时间延迟适应。 Further, according to the I section 7.2.1 and 7.2.2, preferably possible to adapt the delay time during the stimulation.
[0100] 4.放大测量的神经活动。 [0100] 4. The amplified measured neural activity. 测量的神经活动典型地比根据经验导致刺激效果的刺激幅度小几个数量级。 Neural activity is typically measured empirically result in stimulation amplitude ratio of the stimulatory effects of several orders of magnitude. 因为这个原因，必须执行放大，这根据部分7. 2. 3能够在刺激期间适应。 For this reason, the amplification must be performed, which can be adapted during the stimulation partial 7. 2.3. [0101] 5.时间编码测量的神经活动。 [0101] The coded measurement time neural activity. 由于具有大梯度的信号对神经动态具有大影响，所以例如以脉冲串或由短矩形脉冲组成的低或高频脉冲串的形式编码测量的神经活动。 Since the signal has a large dynamic gradient has a large effect on the nerve, the nerve activity for example in the form of a coded bursts or short rectangular pulses or low frequency pulse trains measured. 为了增强刺激的效果，也能够使用其他的编码方法。 In order to enhance the effect of stimulation, it is possible to use other coding methods.
[0102] 6.改变神经活动的极性。 [0102] 6. The neural activity changes polarity.
[0103] 7.线性和/或非线性地变换神经活动。 [0103] 7. A linear and / or nonlinear transforms neural activity. 这能够例如借助于希耳伯特和/或傅立叶(Fourier)和/或小波变换进行。 This can, for example, by means of a Hilbert and / or Fourier (of Fourier) and / or a wavelet transform.
[0104] 8.限制刺激信号的最大幅度。 [0104] 8. The most significant limitation of the stimulation signal.
[0105] 9.以这样的方式变换测量的神经活动：产生其净电荷输入基本上为零的刺激信号。 [0105] 9. In this manner conversion measured neural activity: generating a stimulation signal which is input substantially zero net charge.
[0106] 10.测量的神经活动直接用作反馈刺激信号。 [0106] 10. The measurement of neural activity is directly used as a feedback stimulation signal.
[0107] 通过施加上述处理步骤中的至少ー个组成部分，来确定处理的神经活动，亦即反馈刺激信号。 [0107] By applying ー component of at least the above-described processing steps, the processing of determining neural activity, i.e., the feedback stimulation signal. 例如，能够总是使用相同的处理步骤从测量的神经活动中生成刺激信号。 For example, always use the same process step of generating a stimulation signal from the measured neural activity. 同样，治疗步骤的集合和/或它们的參数能够通过确定性的和/或随机的和/或组合的随机/确定性的算法及时改变。 Similarly, a set of treatment steps and / or parameters thereof can be changed in time by a deterministic and / or random and / algorithms random / deterministic or in combination.
[0108] 3. 4刺激激励的形成 [0108] 3.4 stimulate the formation of excitation
[0109] 刺激激励被理解为这样的刺激激励，其经由电极2施加，并且在时间间隔中起作用。 [0109] stimulation excitation stimulus it is understood as such a stimulus, which is applied via the electrodes 2, and play a role in the time interval. 为了形成刺激激励，使用反馈刺激信号，換言之即根据部分3. 3处理的神经活动。 To form the stimulation stimulus, feedback stimulation signal, in other words, neural activity in accordance with section 3.3 of the process. 为了生成刺激激励，刺激信号例如相互和/或自身相乘、相除、相加和/或相減，和/或借助于其他非线性函数变换。 To generate the excitation stimulus, e.g. stimulation signal with each other and / or self-multiplication, division, addition and / or subtraction, and / or by means of other nonlinear transformation function.
[0110] 神经活动的处理期间使用的时间延迟，例如被限定为将要去耦的振荡神经活动和/或驱动神经活动的周期的分数，并且优选地基本上为周期的N分之一的倍数，其中N是小的整数，例如为2。 [0110] Time used during processing delay neural activity, for example, is defined as the oscillation decoupled neural activity and / or fractional cycle driven neural activity, and preferably substantially a multiple of one cycle of N points, where N is a small integer, for example 2. 刺激信号的时间延迟也能够被选择例如大于刺激周期T。 Time delay of the stimulation signal can also be selected, for example, greater than the stimulation period T. 根据本发明的装置还提供使用若干优选地不同的时间延迟用于形成刺激激励的可能性。 The apparatus of the present invention also provides the use of a number of different possibilities for the time delay is preferably formed to stimulate excitation. 合成的时间延迟反馈刺激信号能够线性和/或非线性地组合以形成刺激激励。 Synthesis of time delay feedback stimulation signal can be a linear / non-linear manner or in combination to stimulate the formation and excitation.
[0111] 为了这个目的，根据本发明的装置具有施加以描述的方式描述的电刺激激励的装置。 [0111] For this purpose, the device according to the invention the applied electrical stimulation apparatus described in the manner described with excitation. 该装置为电极2、控制系统4，其向电极2递送控制信号，用于递送这些激励。 The electrode device 2, the control system 4, a control signal which is delivered to the electrodes 2, for delivery of these incentives. 进而传感器3和用于信号处理的単元4，其接收神经活动并将其准备用于进ー步用作刺激激励。 3 and a further sensor for radiolabeling signal processing unit 4, which receives the neural activity and to prepare it for feeding ー as further stimulation stimulus. 优选地如此生成刺激，其净电荷输入基本上为零。 Preferably the thus generated stimulation, which is substantially zero net charge input.
[0112] 例如，能够以根据部分3. 3的相同处理过的神经活动的形式用相同的刺激驱动电极2。 [0112] For example, according to the same process can be in the form of section 3.3 of the neural activity through the stimulation electrode driven by the same 2. 也能够用不同的刺激信号和/或刺激信号的组合和/或借助于刺激信号的不同变换和/或组合来驱动电极2。 It is possible to use different stimulation signals and / or combinations of the stimulation signals and / or converted by means of different stimulation signals and / or combinations of electrodes 2 are driven.
[0113] 能够借助于确定性的和/或随机的和/或组合的随机/确定性的算法来确定激励的等级和/或类型和/或能量输入和/或參数。 [0113] by means of deterministic and / or random and / algorithms random / deterministic or in combination to determine the level and / or type and / or energy input and / or excitation parameters.
[0114] 处理步骤中使用的刺激激励的时间延迟和/或极性和/或应用周期和/或強度，见部分3. 3，能够系统性地变化或任意控制，換言之即根据确定性的或随机的规则。 Stimulation [0114] The processing steps used in the time delay of the excitation and / or polarity and / or the application period and / or intensity, see section 3.3, can be arbitrarily controlled systematically varied or, in other words, according to deterministic or random rules. 为了这个目的，根据本发明的装置具有以这样的方式编程的控制系统：它确定性地和/或随机地激活刺激激励的处理步骤的时间延迟和/或极性和/或应用周期和/或強度。 For this purpose, a control system is programmed in such a manner the device according to the invention: a time delay and / or polarity and / or the application period and / or its deterministic and / or random excitation activating stimulus processing procedure strength. [0115] 通过改变刺激信号的处理步骤之内的时间延迟和/或极性和/或应用周期和/或強度，能够防止神经元群体的适应过程，其产生刺激強度的增加以便实现相同的治疗效果。 [0115] By changing the time delay and / or polarity and / or the application period and / or intensity of the stimulation signal processing steps, the adaptation process can be prevented neuronal populations which produce increased stimulation intensity in order to achieve the same therapeutic effect. [0116] 电极和传感器的空间布置 Space [0116] electrode and a sensor arrangement
[0117] 4. I刺激电极 [0117] 4. I stimulation electrode
[0118] 电极2优选地用于刺激。 Electrode 2 [0118] preferably used for stimulation.
[0119] 在电极2安置在将要去耦的神经细胞群体中的情况下，电极应当优选地以这样的方式布置：电极能够用于刺激将要去耦的整个神经细胞群体。 [0119] In the case where the electrode 2 is arranged to be decoupled neural cell population, the electrodes should preferably be arranged in such a manner that: the electrode can be used for the entire population of nerve cell stimulation to be decoupled. 这能够通过电极的几何安置来实现。 This can be achieved by placement of the electrode geometry. 例如，电极2能够安置在将要去耦的区域中心。 For example, the electrode 2 can be arranged in the central region to be decoupled. [0120] 在电极2没有安置在将要去耦的神经细胞群体中的情况下，在与以这种形式的刺激将要去耦的区域不同的目标区域中施加刺激。 [0120] In the case where the electrode 2 is not arranged to be decoupled neural cell population, stimulation is applied in this form in a region of stimulation to be decoupled different target regions. 然后通过与将要去耦的神经细胞群体不同的神经元群体的刺激，和/或通过刺激连接到将要去耦的神经细胞群体的纤维束，能够施加间接刺激。 And then by stimulating the nerve cell population to be decoupled different neuronal populations, and / or connected to the fiber bundle to be decoupled by stimulating the population of nerve cells, indirect stimulation can be applied.
[0121] 4. 2传感器的数目 [0121] The number of sensors 4.2
[0122] 根据本发明的装置的机理基本上在于，如部分I和3所述，将要去耦的神经元群体和/或驱动神经元群体的测量过和处理过的神经活动作为刺激被再次施加。 [0122] The mechanism of the device that substantially present invention, as described in Part I and the 3, going neuron population coupled and / or measuring neuron population driven and processed through a neural activity stimulation is reapplied . 传感器3是根据本发明的装置的最重要的部件之一，并且能够或者安置在将要去耦的神经元群体和驱动神经元群体之外，或者优选地直接安置在将要去耦的神经元群体和/或驱动神经元群体内，如部分3. 2所述。 The sensor 3 is one of the most important components of the device according to the present invention, and can be placed in or outside the neuron population and driving neuron population to be decoupled, or preferably directly disposed in the neuron population to be decoupled and / or the driving neuron population, as described in section 3.2. 只有一个传感器3优选地用于检测将要去耦的神经元群体和/或驱动神经元群体的活动。 Preferably only one sensor 3 for detecting the neuron population to be decoupled and / or the driving neuron population activity. 結果，将要植入的传感器的数目保持得尽可能地少，以便防止植入期间的不必要的组织伤害并且尤其是脑出血。 As a result, the number of sensors to be implanted is kept as low as possible, in order to prevent unnecessary tissue damage during implantation and in particular cerebral hemorrhage. 然而，例如同样能够使用两个或多个传感器，以便作为测量活动的组合完全得多地重构将要去耦的神经元群体和/或驱动神经元群体的神经活动。 However, for example, two or more of the same sensors can be used to fully reconstruct much of the neuron population to be decoupled and / or neural activity driven neuron population as a combined measure of activity.
[0123] 进而，通过在ー个将要植入的电极中组合至少ー个传感器3和刺激电极2，植入所造成的可能大脑伤害被进ー步減少或避免，并且改善了刺激效果。 [0123] Further, by combining the two electrodes ー ー to be implanted in at least one sensor 3 and the electrode 2 may stimulate the brain damage, caused by implanted into ー further reduced or avoided, and improved stimulatory effect.
[0124] 在传感器3全部安置在将要去耦的神经细胞群体和/或驱动神经细胞群体内的情况下，应当优选地以这样的方式布置传感器3 :借助于传感器能够覆盖大比例的将要去耦的神经细胞群体和/或驱动神经细胞群体。 [0124] In the sensor 3 are all disposed in the decoupled or neural cell population and / or drive situation within the nerve cell population, it should preferably be disposed in such a way that the sensor 3: by means of a sensor can cover a large proportion of the decoupled the nerve cell population and / or driven nerve cell population. 这能够用传感器关于将要去耦的组织和/或驱动组织的几何布置来实现。 This sensor can be used on the tissue and / or tissue to be decoupled driving geometric arrangement is achieved. 在用只有一个传感器3布置的情况下，后者例如能够位于组织的中心。 In the case of using only one sensor arrangement 3, which is for example located in the center of the tissue. 在用若干传感器布置的情况下，例如能够以对称的方式布置传感器。 In the case of using several sensors are arranged, for example, a sensor can be arranged in a symmetrical manner.
[0125] 在传感器3中的至少ー个没有安置在将要去耦的神经细胞群体和驱动神经细胞群体内的情况下，在与以这种形式的活动测量的将要去耦的区域和驱动区域不同的至少ー个区域中，測量与将要去耦的神经元群体和/或驱动神经元群体的神经活动相关联的活动。 [0125] The sensor 3 is not disposed in at least one ー in the case of driving neural cell population to be decoupled and neural cell populations, with different forms of activity measurement in this region will be decoupled, and the drive region the ー least one region, and measured the neuron population to be decoupled and / or active neuron population driven neural activity associated. 如部分3. 2所述，通过测量与将要去耦的神经细胞群体和驱动神经细胞群体不同的神经元群体和/或连接到将要去耦的神经细胞群体/驱动神经细胞群体的纤维束和/或身体部位的活动，能够实现间接测量。 As described in Section 3.2, by measuring the different neural cell populations to be decoupled and the driving nerve cell population of neuronal groups and / or fiber bundle is connected to the neural cell population to be decoupled / driving nerve cell populations and / body parts or activities, to achieve indirect measurement.
[0126] 5.刺激信号的自调节的需求控制 [0126] The demand for a self-regulating control stimulation signal
[0127] 根据本发明的装置的机理的最重要特性之ー是刺激信号的自调节的需求控制。 [0127] self-regulating demand stimulation signal in accordance with a control mechanism ー most important features of the apparatus of the present invention. 描述的自调节由于刺激激励由处理过的神经活动组成的事实而发生。 Described self-regulating due to the stimulation by the fact that the excitation treated neural activity of the composition occurs. 在将要去耦的区域中更加強烈的同步活动和/或与将要去耦的区域的驱动群体耦合的情况下，必须预期測量神经活动的大变化，如专家已知的那样。 In the area to be decoupled more strongly in synchronous activity and / or large changes in the case of the driving population to be decoupled area coupling it must be expected to measure neural activity, such as expert known. 这直接导致刺激根据本发明时间延迟，具有増加的刺激幅度。 This is a direct cause irritation to the present invention according to a time delay, of having to increase in stimulation amplitude. 根据本发明，并且说明性地，施加的刺激信号的力补偿了内部同步和/或与将要去耦的区域的驱动群体的耦合的力，导致将要去耦的群体的去耦和去同歩。 According to the present invention, and illustratively, the force applied to the stimulation signal compensates for the internal synchronization and / or the area to be decoupled driving force coupling groups, resulting in decoupling decoupled to the same groups and ho. 结果，对将要去耦的群体的合成刺激影响、亦即刺激和耦合之和的幅度被独立地最小化。 As a result, the synthesis of stimulation on the population to be decoupled, i.e. the coupling and the stimulation amplitude and independently minimized. 在已实现去耦和去同步之后，预期小变化的神经活动，作为其结果，刺激信号被直接影响并独立地适应。 After having decoupled and desynchronized, small changes in neural activity expected, as a result of the stimulation signal is directly influenced and independently adapt. 如果新的耦合和/或再同步再次发生，则根据本发明的装置自动考虑对去耦和/或去同步刺激的增加需求：更大变化的神经活动导致形成更强的刺激。 If a new coupling and / or resynchronization occurs again, the automatic consideration of decoupling and / or desynchronization increased demand stimulation apparatus according to the invention: neural activity greater variation leads to a stronger stimulus. 这代表了根据本发明的装置的自调节的需求控制。 This represents a self-regulating in accordance with the needs of the control apparatus of the present invention.
[0128] 形成自调节的需求控制的基础的机理，在随后的文本中更加详细地描述的根据本发明的装置的全部实施例中都起作用。 [0128] self-regulating based on the formation mechanism of demand-controlled, are to function as described in more detail in the text which follows embodiment of the apparatus according to all embodiments of the present invention.
[0129] 6.激励应用的控制 [0129] 6. The application of an excitation control
[0130] 激励应用的时间控制被理解为事先优选地编程的根据本发明的装置的实施例，所述刺激激励借助于刺激器単元8以特殊的方式施加。 Time [0130] excitation control application is understood to be programmed in advance in accordance with a preferred embodiment of the device according to the present invention, by means of the stimulation excitation radiolabeling stimulator unit 8 is applied in a special way. 激励应用的时间控制的变体是持久、 重复和需求控制的激励应用。 Variant time-controlled excitation is applied to persistent and repeated excitation control applications. 另外，例如对于患者或医生所执行的激励应用，能够实行手工需求控制。 Further, for example, the patient or physician stimulus application executed, it is possible to implement the demand control manually.
[0131] 6. I持久激励应用 [0131] 6. I persistent stimulus application
[0132] 在持久激励应用中，根据本发明的装置具有以这样的方式编程的控制系统：它在电极2处执行刺激的连续应用。 [0132] in a persistent excitation applications, with a control system programmed in such a manner the device according to the invention: it performs a continuous application at the stimulation electrode 2. 持久激励应用代表了根据本发明的装置的最简单和容易实行的实施例。 Persistent stimulus application represents the most simple and easy to implement the embodiment of the device according to the invention. 与此同吋，由于部分5中描述的根据本发明的自调节的需求控制，持久刺激以输入到将要去耦的群体中的很少能量产生良好的去耦和去同步效果。 At the same inch, since the present invention is self-regulating demand control described in section 5 and lasting for input to the stimulation little energy and produce good decoupling to synchronization effect decoupled population.
[0133] 在持久激励应用期间，根据部分7. 2. 3能够使强度參数适应。 [0133] During the persistent stimulus application, partial 7. 2.3 strength parameters can be adapted. 类似地，时间參数——刺激周期T和/或时间延迟，根据部分7. 2. I和7. 2. 2，能够与刺激強度的适应联合或者其独立地在持久刺激期间适应。 Similarly, the time parameter - stimulation period T and / or time delay, in accordance with section 7.2.1 and 7.2.2 the I, can be combined with the stimulation intensity adapt it alone, or during a persistent stimulation adaptation.
[0134] 6. 2重复激励应用 [0134] 6.2 Application of repeated excitation
[0135] 在重复激励应用中，根据本发明的装置具有以这样的方式编程的控制系统：它仅在特定的时间间隔期间在电极2处执行刺激激励的应用。 [0135] In the repeated application of the excitation, having a control system programmed in such a manner the device according to the invention: it is only applied stimulation at the excitation electrode 2 is performed during a specific time interval. 在这些时间间隔之外没有刺激。 No stimulation outside these time intervals. 在重复激励应用中，能够在时间方面严格周期性地或时间方面非周期性地给予刺激激励。 Repeating stimulus application, the time strictly periodically or non-periodically giving a stimulus excitation aspects in terms of time. 在这个实施例中，根据本发明的装置具有以这样的方式编程的控制系统：它周期性地和/或非周期性地控制刺激间隔之间的时间间隔和/或间隔的持续时间。 In this embodiment, the apparatus of the present invention has such a manner programmed control system: it periodically and / or aperiodically to control the duration of the interval between the stimulus interval and / or spacing. 刺激的时间非周期性序列能够通过随机和/或确定性和/或组合的随机/确定性的算法来生成，以便实现将要去耦的群体的预期去耦和去同步状态。 Aperiodic stimulus time series can be generated by random and / or deterministic and / or stochastic algorithm / deterministic or in combination, in order to achieve the desired population to be decoupled and desynchronized decoupled state. 类似地，在随后的文本中，确定性和随机规则的组合被理解为这样的函数关系，其中，确定性和随机术语例如通过加法和/或乘法用函数式相互链接。 Similarly, in the text which follows, the deterministic and random combination rule is understood to be a function in which, for example, by the term deterministic and random addition and / or multiplication by each functional link.
[0136] 刺激和测量间隔能够布置得交迭或同时发生或在时间上分开。 [0136] stimulation and measurement interval can be arranged separately or simultaneously or overlapping in time. 在重复激励应用期间，強度參数能够根据部分7. 2. 3适应。 Excitation during repeated use, can accommodate a partial intensity parameter 7. 2.3. 类似地，时间參数——刺激周期T和/或时间延迟，根据部分7. 2. I和7. 2. 2，能够与刺激強度的适应联合或者其独立地在重复刺激期间适应。 Similarly, the time parameter - stimulation period T and / or time delay, in accordance with section 7.2.1 and 7.2.2 the I, can be combined with the stimulation intensity adapt independently or in adaptation during repeated stimulation.
[0137] 6. 3需求控制的激励应用 [0137] 6.3 Application of excitation of the demand control
[0138] 在需求控制的激励应用中，根据本发明的装置具有以这样的方式编程的控制系统：它根据将要去耦的神经元群体和/或驱动神经元群体的特殊状态执行刺激的接通和断开。 [0138] In the excitation control application requirements, the device according to the invention has such a manner programmed control system: it performs the special stimulation ON state of the neuron population to be decoupled and / or the driving neuron population and disconnect. 为了这个目的，控制单元4使用測量信号和/或刺激信号用于检测病理性特征。 For this purpose, the control unit 4 uses the measurement signal and / or stimulation signals for the rational feature detection disease. 例如如随后的文本中描述的那样接通刺激。 For example, as text is turned stimuli such as described in the following. [0139] 经由传感器3来测量将要去耦的神经元群体和/或驱动群体的活动。 [0139] measured via the sensor 3 to be decoupled neuron population and / or event driven groups. 神经活动被前转到用于信号处理和/或控制的単元4，其尤其充当用于检测病理性特征的装置。 The neural activity signal processing and / or radiolabeling unit 4, which serves as a means for controlling in particular feature rational for detecting the disease prior to. 用于信号处理和/或控制的単元4 一旦在神经活动中检测到病理性特征，就启动刺激激励的应用。 For signal processing and / or use in radiolabeling unit 4 upon detecting neural activity to rational wherein the disease, stimulation stimulus is started control. 病理性特征由于施加刺激的效果而一旦消失，就优选地断开刺激。 Pathological characteristics due to the effect of the applied stimulation ceases, it is preferably disconnected stimulation. 根据本发明的装置因此在ー个可能的实施例中包含计算机作为用于信号处理和/或控制的単元4，所述计算机包含数据介质，其携帯疾病模式的数据并将它与测量数据相比较。 The thus ー possible embodiment of the device according to the present invention contains a computer for signal processing and / or radiolabeling unit 4, the control computer comprises a data medium carrying data Bands disease pattern and compares it with the measured data . 疾病模式的数据被理解为与刺激相关的參数和测量变量，例如经由传感器3测量的神经活动的瞬时频率、对于需求控制的激励应用的过程所必要的阈值、限定激励強度的刺激參数。 Data is understood as a disease model associated with the stimulus parameters and measured variables, e.g., via the instantaneous frequency of the neural activity measured by the sensor 3, the process for the excitation of the application requirements necessary to control the threshold value, the stimulation parameters defining the excitation intensity. 病理性特征被理解为例如将要去耦的神经元群体和/或驱动神经元群体的疾病相关的同歩，并且能够通过神经活动的以下特性识别： Pathological features are understood, for example, the neuron population to be decoupled and / or the drive with the ho diseases related to neuron population, and can be identified by the following characteristics nerve activity:
[0140] a)如果经由传感器3，专有地或突出地为将要去耦的神经元群体和/或驱动神经元群体的病理性活动，其如例如部分3. 2和部分4. 2中描述的直接測量中那样被測量，则神经活动直接用于确定神经活动的幅度是否超过阈值。 [0140] a) If, as for example in which 3.2 part and 4.2 part 3 via the description, or exclusively be decoupled for projection neuron population and / or pathological activity sensor driving neuron population as in a direct measurement is measured, the neural activity was used directly in the neural activity to determine whether the amplitude exceeds a threshold value. 在优选实施例中，根据本发明的装置因此装备有用于检测对应于阈值的神经活动的幅度值的装置。 In a preferred embodiment, the device according to the invention therefore equipped with an amplitude value corresponding to a threshold value for detecting a neural activity means. 在这种情况下，神经活动自身和/或其量和/或其幅度优选地与阈值相比较。 In this case, the neural activity itself and / or the amount thereof, and / or preferably the amplitude is compared with a threshold value. 在这个实施例中，能够以这样的方式编程用于检测阈值的装置：它将例如神经活动自身和/或其量和/或其幅度与阈值相比较。 In this embodiment, it is possible to program such a manner that the means for detecting a threshold: for example, it neural activity itself and / or the amount thereof and / or its amplitude is compared with a threshold value. 或者通过确定信号的量以简单的方式和/或使用带通滤波和/或希耳伯特变换和/或小波分析来确定幅度。 Or an amount determined by the amplitude of the signal determined in a simple manner and / or band-pass filtering and / or a Hilbert transformation and / or wavelet analysis. 在这种情况下，以这样的方式编程用于信号处理的単元4 :它能够执行信号量的确定和/或带通滤波和/或希耳伯特变换和/或小波分析。 In this case, in a manner programmed for radiolabeling signal processing unit 4: it can be performed to determine the amount of signal and / or a bandpass filtering and / or / or a wavelet analysis and Hilbert transform. 特别优选地使用神经活动或其量，因为幅度的计算意味着显然更高的计算工作量，并且幅度不能在神经活动的单个测量值上面确定，而是必须在对于专家已知的足够大的时间间隔中确定，这能够略微延迟病理性特征的检测。 Particularly preferably used, or the amount of neural activity, apparently because the calculated mean magnitude higher computational effort, and the amplitude can not be determined in a single measurement of neural activity above but must be known to the expert in a sufficiently large time interval is determined, it is possible to detect a slight delay in disease rational features.
[0141] b)如果除了将要去耦的神经元群体和/或驱动神经元群体的这种病理性活动之夕卜，例如从其他神经元群体经由传感器3还另外測量非疾病特定的活动，像例如部分3. 2和4. 2中描述的间接測量中那样，则必须在神经活动的分析中插入进一歩的算法步骤。 [0141] b) If in addition to the neuron population to be decoupled and / or evening activities such pathological drive Bu neuron population, e.g. additionally measured via the non-disease specific activity sensor 3 from other neuronal populations, such as as example, the algorithm must be inserted into a ho step in the analysis of neural activity indirectly measuring section 3.2 and 4.2 described herein. 由于疾病特定的活动典型地在与非疾病特定的活动的频率范围不同的频率范围内发生，所以为了这个目的优选地执行疾病特定的频率范围内的活动估计是足够的。 Due to disease specific activity typically occurs in different activities and non-disease specific frequency range of the frequency range, for this purpose it is preferable to perform activities within a frequency range of a particular disease is estimated to be sufficient. 例如通过确定连续触发点的差来确定疾病特定活动的频率。 E.g. disease-specific activity is determined by the frequency determining the difference between successive trigger point. 触发点是诸如最大值、最小值、转折点和零过渡之类的点。 Trigger point such as maximum, minimum, inflection point of transition and zero like points. 这种分析优选地在滑动时间窗口中执行，形成增加稳定性的若干时间差的平均值。 This analysis is preferably performed in a sliding time window, the time to increase the stability of the formed plurality of differences of mean values. 作为选择，频率也能够用对于专家已知的频谱估计方法和像例如借助于傅立叶分析之类的其他频率估计器来估计。 Alternatively, it is possible for the frequency spectrum estimation methods known to the expert, like for example, and other frequencies by means of Fourier analysis estimator to such estimation. 为了这个目的，根据本发明的装置在特殊的实施例中具有用于估计疾病特定频率范围内活动的手段，诸如频谱估计方法、傅立叶和/或小波分析等。 For this purpose, the device according to the invention has a means for estimating the activity of disease-specific frequency range in a particular embodiment, the spectral estimation methods such as Fourier and / or wavelet analysis. 这例如通过用于执行频率分析的装置实行。 This means, for example, implemented by performing frequency analysis. 例如，能够在滑动窗口中确定疾病特定频率范围内的频谱能量。 For example, it is possible to determine the spectral energy within a specific frequency range of diseases in the sliding window. 作为选择，在带通滤波之后，通过确定带通滤波信号的最大值，或者通过确定带通滤波信号的量的平均值，和/或通过希耳伯特变换和/或通过小波分析，能够确定疾病特定频率范围内的幅度。 Alternatively, after bandpass filtering, by determining the maximum value of the band-pass filtered signal, or by determining the average value of the band-pass filtered signal amounts, and / or by a Hilbert transformation and / or wavelet analysis can be determined the amplitude of the specific frequency range of diseases. 为了这个目的，根据本发明的装置具有例如用于带通滤波幅度的装置和用于确定带通滤波信号最大值的装置和/或用于确定带通滤波信号的量的平均值的装置和/或用于执行希耳伯特变换和/或小波分析的装置。 For this purpose, the device according to the amplitude of the band-pass filter device of the present invention has, for example, and the means for determining the maximum band-pass filtered signal and / or means for the average amount of the band-pass filtered signal is determined and / or means for Hilbert transformation and / or wavelet analysis is performed.
[0142] 在需求控制的激励应用的情况下，例如总是使用相同的刺激激励。 [0142] In the case of excitation of the control application requirements, for example, always use the same stimulation stimulus. 刺激周期T如部分7. 2. I所述优选地适合于将要去耦的神经元群体和/或将要驱动的神经元群体的瞬时频率。 The stimulation period T of the portion 7. 2. I is preferably adapted to the instantaneous frequency and / or to be driven neuron population to be decoupled neuron population. 当病理性特征存在吋，然后以适合于瞬时频率的刺激周期T施加激励。 When there inch pathological features, and suitable for the stimulation period T to the instantaneous frequency excitation is applied. 类似地，根据部分7. 2. 2能够使时间延迟适应，并且/或者这种激励的強度优选地保持不变。 Similarly, according to section 7.2.2 it is possible to adapt the delay time, and / or the intensity of this excitation is preferably maintained. 然而，強度參数也能够根据刺激效果而修改，如部分7. 2. 3中那样。 However, the intensity parameters can be modified according to the effect of stimulus, such as in section 7. 2.3.
[0143] 6. 3. I确定需求 [0143] 6. 3. I determined requirements
[0144] 为什么在病理性特征的实例和疾病特定症状的实例之间没有明确的关系存在至少两个原因。 [0144] Examples reason why the characteristics between instances of disease and disease-specific symptoms without at least two reasons why there is a clear relationship. 一方面，传感器3从将要去耦的区域和/或其中生成将要测量的神经活动的驱动区域的距离，导致疾病特定频率范围内幅度的变化。 In one aspect, the sensor 3 and the distance from the area to be decoupled / or wherein generating neural activity to be measured in the driving area, resulting in changes in the amplitude of the specific frequency range of diseases. 另ー方面，疾病特定特征的特殊实例，換言之即疾病特定频率范围内有节律活动的实例，并不明确地与疾病特定症状相关联。 Another aspect ー, specific examples of disease-specific characteristics, i.e., in other words there are instances rhythmic activity in disease-specific frequency range, it is not clearly associated with disease-specific symptoms. 由于疾病特定节律对大脑中的复杂神经网络具有影响，其另外典型地并不遵守简单线性动态规则，所以在疾病特定节律和症状的实例之间没有明确的关系。 Since the disease-specific rhythm in the brain has an effect on the complex neural network, which typically do not additionally simple linear dynamic compliance rules, there is no clear relationship between instances of disease-specific symptoms and rhythm. 如果例如疾病特定节律没有充分对应于末端的生物力学确定的固有频率，则与如果疾病特定节律与末端的生物力学预定的固有频率共振相比，疾病特定节律所造成的震颤显然较少。 If, for example disease-specific rhythm does not sufficiently correspond to the natural frequency determined biomechanical terminal, and if the disease-specific rhythm end biomechanical predetermined natural frequency of resonance compared to disease-specific rhythm tremor caused distinctly less.
[0145] 像例如测量的神经活动的主频率和幅度之类的特性处于对专家已知的经验范围内。 [0145] properties such as frequency and amplitude of the main class of neural activity is measured within the range of experience known to the expert. 经由传感器3测量的神经活动的疾病特定特征的实例的值被称作阈值，它的越界(transgression)典型地引起例如震颤的症状发生。 Examples of diseases via the value of the specific features of neural activity measured by the sensor 3 is referred to as a threshold value, it bounds (Transgression) e.g. typically causes symptoms of tremor. 阈值是必须为部分6. 3中描述的需求控制的激励应用的实施例选择的參数。 Parameter threshold is a selected embodiment of the embodiment must be controlled excitation is applied demand section 6.3 below. 根据本发明的装置因此以控制単元4的形式包含用于检测阈值的装置。 Thus the device according to the invention means for detecting the threshold value as the control unit 4 comprises means for radiolabeling. 根据本发明的需求控制的激励应用的方法实现了下述优点：根据本发明的装置的有效性并不决定性地取决于阈值的选择，而是考虑关于阈值选择的大的容错，其处于例如直到疾病特定特征最大实例的50%的范围之内。 The method of excitation to achieve application requirements of the present invention controls the following advantages: depending on the selection threshold based on the validity of the apparatus of the present invention is not decisive, but considering the large fault tolerant on the selected threshold, for example, until it is in within the range of 50% of the maximum specific examples of disease characteristics. 或者在外科手术进行时，或者优选地在手术之后的第一次情况下，通过经由传感器3測量神经活动，以确定疾病特定特征的实例并与例如震颤强度的症状实例相比较的方式，确定阈值的选择。 Or intraoperatively, or preferably in the first case after surgery, by way of example measuring the neural activity via the sensor 3, to determine disease-specific characteristics with e.g. manner symptoms Examples tremor intensities compared to determine the threshold value s Choice.
[0146] 在需求控制的激励应用的较少优选的实施例中，阈值被取为代表性的值，例如患者中测量的阈值集体的平均值。 [0146] In the demand control excitation applied less preferred embodiment, the threshold value is taken as a representative value, for example, the average threshold value in the patient collective measurement. 在优选实施例中，阈值的选择在基本上规则的间隔中检查，例如在每半年的控制期间。 Embodiment, the selection threshold is checked at substantially regular intervals in the preferred embodiment, for example, every six months during the control.
[0147] 在部分6. I和6. 2中描述的具有需求控制激励強度的持久和重复刺激的实施例中，阈值检测是不必要的。 [0147] In the section 6. I and persistent and repetitive stimulation embodiment of the control having the excitation intensity demand 6.2 described threshold detection is unnecessary.
[0148] 能够优选地在与部分7. 2中描述的用于使刺激參数适应的方法的不同组合中使用上述三种刺激方法。 [0148] can be preferably used as in section 7.2 of stimulation methods described adaptation of the parameters used in the combination of the three different stimulation methods.
[0149] 全部三种刺激方法共同具有固有的根据本发明的自调节的需求控制。 [0149] All three methods of co-stimulation is inherently self-regulating control of the present invention according to demand. 刺激信号对测量的神经活动的直接依赖使部分5中描述的自调节的需求控制成为必要，作为其結果，输入到将要去耦的群体中的能量被最小化。 Direct stimulation signal dependent on the measurement of neural activity that the self-regulating demand control section 5 described becomes necessary, as a result, the energy input into the decoupled population is minimized. 这种自调节的需求控制独立于部分6. 3中描述的另外需求控制的实行和如部分7所述的參数的校准与控制而起作用。 Further demand for such self-adjusting independently demand control described in section 6.3 and the implementation of control of the calibration control section 7 which function parameters.
[0150] 參数的校准和适应 [0150] adaptation and calibration parameters
[0151] 在随后的文本中，假定电极2位于将要去耦的神经元群体内。 [0151] In the text which follows, it is assumed 2 is located within the neuron population to be decoupled electrode. 电极位于将要去耦的神经元群体之外的情况在该部分的末尾分开考虑。 The case where the electrodes are located outside the neuron population to be decoupled considered separately at the end of the portion. 能够对根据本发明的装置的以下參数执行校准和适应，例如：其倒数对应于刺激周期的刺激信号的频率、刺激信号的时间延迟和刺激激励強度。 Able to perform the calibration and adaptation of the following parameters of the device according to the present invention, for example: the reciprocal stimulation period corresponding to a frequency of a stimulation signal, the time delay of the stimulation signals and stimulation stimulus intensity.
[0152] 7. I刺激开始时的刺激參数[0153] 7. I. I频率、刺激周期 [0152] 7. I stimulation stimulation parameters at the beginning [0153] 7. I. I frequency stimulation period
[0154] 装置的没有事先操作的频率选择：对于各个疾病模式，病理性神经活动的频率范围对专家是已知的(Elble, RJ and Roller WC (1990) ： Tremor, John HopkinsUniversity Press, Baltimore)。 [0154] the frequency selection operation of the device without previously: for each disease pattern, the frequency range of the pathological neural activity are known to the expert (Elble, RJ and Roller WC (1990): Tremor, John HopkinsUniversity Press, Baltimore). 关于这种频率范围，能够优选地取平均值。 About this frequency range, can preferably be averaged. 作为选择，能够代替地使用与年龄和性别相关的预期频率值。 Alternatively, it is possible instead to use the expected frequency value associated with age and gender.
[0155] 为了根据本发明的装置的成功操作，不必要的是，初始预定的频率对应于将要去耦的神经元群体的活动或驱动神经元群体的活动的频率，实际存在。 [0155] For successful operation of the device according to the present invention, is not necessary, a predetermined initial frequency corresponds to the frequency of the active neuron population to be decoupled driving neuron population or activity, actually exists. 即使当使用大大偏离正确频率值的初始值时，在7. 2. I描述的刺激周期T的控制也起作用。 Even when the initial value is largely deviated from the correct frequency values ​​also play a role in the control of the stimulation period T 7. 2. I described. 大大偏离意味着值也能够以至少10的因数而太大或太小。 Means that the value can be greatly deviated from a factor of at least 10 being too large or small. 作为选择，从而也可以优选地以处于疾病典型的并对专家已知的频率范围之内的频率值开始。 Alternatively, such a frequency may preferably be a value within the experts in the disease and typical known frequency range begins. 同样能够优选地通过对各个患者単独的适应来获得刺激开始时的频率值。 Likewise preferably obtained frequency at the start of stimulation by adaptation to the individual patient unique radiolabeling. 这能够例如通过为刺激作准备的如部分6. 3所述的将要去耦的神经元群体和/或驱动神经元群体的活动的神经活动测量和主频率估计来实现。 This can be achieved by, for example, as will be decoupled portion of the neuron population to 6.3 and / or neural activity measurement and a main frequency of the drive active neuron population stimulated to prepare estimates.
[0156] 装置的具有事先操作的频率选择：用于频率的开始值被选择为装置的在先操作期间频率的平均值。 [0156] device having a pre-selected frequency of operation: starting value for the average frequency of the frequency is selected to the device during the previous operation.
[0157] 在两种情况下，換言之即具有和不具有装置的事先操作，刺激周期T被计算为频率开始值的倒数。 [0157] In both cases, in other words with and without pre-operation means, the stimulation period T is calculated as the inverse of the frequency start value.
[0158] 7. I. 2时间延迟 [0158] 7. I. 2 time delay
[0159] 刺激信号的时间延迟优选地在刺激频率或刺激周期T的第一确定之后分别确定。 It was determined after the [0159] time delay of the stimulation signal is preferably determined in a first stimulation frequency or the stimulation period T. 时间延迟优选地被选择为刺激周期T的分数，例如T/2。 A time delay is preferably selected to be a fraction of the stimulation period T, for example T / 2. 优选地，也能够选择这样的时间延迟，其对应于刺激周期T的分数的倍数，并且可能超过刺激周期T。 Preferably, it is also possible to select such a delay time, which corresponds to a multiple stimulation period T score, and may exceed the stimulation period T. 部分7. 2. 2中描述的时间延迟的适应在上述情况下也起作用，其中，从其中生成刺激激励的反馈刺激信号的时间延迟的至少ー些不同于和/或超过了刺激周期T。 Time described in section 7.2.2 also work to adapt the delay in such a case, wherein, wherein the time delay generated from the stimulation excitation signal feedback stimulation ー different from at least some of and / or exceeds the stimulation period T.
[0160] 7. I. 3 强度 [0160] 7. I. 3 Strength
[0161] 确定刺激激励的強度的刺激參数（例如反馈刺激信号的放大率）的开始值根据对专家已知的实验值来确定（例如最大幅度10V)。 [0161] stimulation parameters determining the intensity of the excitation stimulus (e.g., feedback stimulation signal amplification factor) to determine a start value (e.g. maximum amplitude 10V) based on experimental values ​​known to the expert. 如果使用大大不同于最优强度值的开始值，在7. 2. 3描述的强度控制同样起作用。 If the start value differ greatly from optimum intensity value, the intensity control 2.3 7 described work equally well. 大大不同意味着值也能够以至少10的因数（优选地最大幅度10V)而太大或太小。 Means that the value can be significantly different by a factor (preferably the most significant 10V) being at least 10 too large or small. 作为选择，从而也可以优选地以处于对专家已知的范围之内的强度值开始。 Alternatively, and thus it may preferably be at the beginning of the intensity values ​​within the range known to the expert. 特别地，优选以刺激信号的小强度值、例如0. 5V的最大幅度开始刺激，以便因而可能減少刺激的副作用。 In particular, preferably a small stimulation signal strength values, for example the maximum amplitude of 0. 5V start stimulation, to thus reduce the possible side effects of irritation. 如果存在使用更强刺激信号的必要性，则能够以小的步长增加強度，如部分7. 2. 3所述。 If the necessity of using a stronger stimulus signal is present, it is possible to increase the strength of small steps, as described in Section 7. 2.3.
[0162] 用于频率和強度的开始值因而能够被预定，并且特别地，并不需要作为耗时校准的部分而被确定。 [0162] start value for the frequency and intensity can thus be predetermined, and in particular, does not require a time-consuming part of the calibration is determined.
[0163] 7. 2刺激參数的适应 [0163] 7.2 adapt stimulation parameters
[0164] 7. 2. I刺激周期T的适应 [0164] 7. 2. I adapt the stimulation period T
[0165] 在将要去耦的区域中和/或驱动区域和/或功能上紧密连接到其的区域中，神经活动被測量，其在处理之后，用作刺激信号。 [0165] In the region of the tight junctions, or to be decoupled and / or on the drive region and / or function thereof to the region, the neural activity is measured which, after processing, is used as the stimulation signal. 例如，在帕金森病中，除了经由传感器3直接在将要去耦的区域中和/或驱动区域中測量之外，还能够经由外皮质传感器在例如皮质运动前区的跟随区域中測量活动。 For example, in Parkinson's disease, in addition to the sensor 3 directly and / or measured in the region of the drive region to be decoupled via the addition, it is possible through the outer cortical region of the front sensor, for example, following the motor cortex in the measurement activity. 在具有下面限定的长度的时间窗口中，确定主要平均周期。 Time window having a length defined in the following, the averaging period is determined mainly. 为了这个目的，能够使用不同的算法。 For this purpose, it is possible to use different algorithms. 例如，刺激周期T能够适合于将要去耦的神经元群体和/或驱动神经元群体的瞬时周期。 For example, the stimulation period T can be adapted to the neuron population to be decoupled and / or the instantaneous period of the driving neuron population. 例如，瞬时周期能够被确定为测量的神经活动的两个连续最大值之间的时间差。 For example, the transient period can be determined as a measure of neural activity two successive time difference between the maximum value. 同样，例如，能够首先估计神经活动的平均频率，并且刺激周期T能够被确定为平均频率的倒数。 Also, for example, it is possible to estimate the average frequency of the first neural activity, and stimulation period T can be determined as the reciprocal of the mean frequency. 如果经由传感器3测量的不仅仅是疾病特定活动，则对于这种类型的频率估计，首先必须经由对疾病特定的频率范围的带通滤波提取疾病特定活动。 If the frequency estimate for this type of disease-specific activity is not only via the measuring sensor 3, the first disease-specific activity must be extracted via a band pass filter for the frequency range of a particular disease. 作为选择，例如，能够经由部分6. 3中提到的频率估计器确定频率。 Alternatively, for example, the frequency can be determined via the frequency estimator mentioned in section 6.3. 用于这种频率估计的时间窗ロ具有这样的长度，其能够朝向上限值打开，并且对应于病理性活动的例如10000个周期，优选地为1000个周期，特别优选地为100个周期，但同样可以是其他任意值。 This time window for the frequency estimation ro have a length, which can be opened toward the upper limit value, and corresponds to the pathological activity of e.g. 10,000 cycles, preferably for 1000 cycles, particularly preferably 100 cycles, but it can also be any other value.
[0166] 7. 2. 2时间延迟的适应 [0166] 7. The time delay adaptation 2.2
[0167] 如部分3. 4和7. I. 2所述，刺激信号的时间延迟优选地被选择为刺激周期T的分数。 [0167] The said portion 3.4 and 7. I. 2, the time delay of the stimulation signal is preferably selected to be the stimulation period T score. 在刺激期间，时间延迟能够例如是固定的，或者优选地适合于根据部分7. 2. I适应的刺激周期。 During the stimulation, for example, a time delay can be fixed, or preferably adapted to accommodate part 7. 2. I according to the stimulation cycle. 为了能够用很少的合成刺激影响实现最佳去耦和/或去同步，刺激信号的时间延迟优选地通过确定性或随机和/或组合的随机/确定性的算法在刺激期间改变。 In order to enable the synthesis with little stimulation in the best decoupling and / or desynchronization, stimulation time delay signal is preferably varied during the stimulation by stochastic and deterministic or stochastic algorithm / deterministic / or combinations thereof. 为了这个目的，根据本发明的装置以控制単元4的形式包含允许刺激信号的时间延迟在刺激期间变化的装置。 For this purpose, the device according to the invention in the form of radiolabeling control unit 4 comprises a stimulation signal to allow time during the stimulation device changes the delay. 进而，能够例如不仅在刺激周期之内而且作为若干周期的部分改变时间延迟。 Further, it is possible, for example, but not as part of changing the time delay of several cycles in the period of stimulation. 在这种情况下，刺激信号对应于较早几个周期时已测量的神经活动。 In this case, when the stimulation signal corresponding to neural activity in several cycles earlier has been measured.
[0168] 7. 2. 3强度的适应 [0168] 7. The intensity adaptation 2.3
[0169] 通过传感器3測量这样的神经活动，其表示将要去耦的神经元群体和/或驱动神经元群体的活动。 [0169] 3 through the measuring sensor such neural activity, which shows a neuron population to be decoupled and / or the driving neuron population activity. 这种神经活动被前转到用于信号处理和/或控制的単元4。 This neural activity is transferred to a signal processing and / or control unit 4 before radiolabeling. 用于信号处理和/或控制的単元4执行根据部分6的持久或重复或需求控制的刺激，其中在各个时间施加的刺激激励的強度取决于神经活动中病理性特征的实例。 For signal processing and / or control unit 4 radiolabeling performed depending on the example of neural activity in accordance with pathological features or repeated or persistent stimuli demand control section 6, wherein the stimulation is applied at various times of the excitation intensity. 为了这个目的，优选地刺激激励的強度能够被适应。 For this purpose, the excitation intensity of stimulation can be preferably adapted. 在这个实施例中，装置包含以这样的方式编程的控制系统：它根据部分3. 3改变测量信号的放大率，用于控制激励強度。 In this embodiment, the apparatus comprises such a manner that programmed control system: it changes the amplification factor of the measurement signal in accordance with section 3.3, for controlling the excitation intensity. 能够取决于刺激结果或者手工或者自动地控制激励強度和病理性特征的实例之间的关系。 Stimulation results can depend either manually or automatically control the relationship between the intensity of the excitation examples and pathological features. 在自由可选择的、优选地不变长度的时间窗口中，其在各个激励之前的恒定时间间隔中结束，以以下方式确定病理性特征的实例： Free Alternatively, the time window is preferably the same length, constant time intervals prior to the end of its respective excitation, wherein determining rational way of example in the following diseases:
[0170] a).在专有地或突出地将要去耦的病理性活动和/或驱动病理性活动经由传感器3测量的情况下，幅度对应于将要去耦的神经元群体的同步实例。 [0170] a). Protrude exclusively or pathological activity going coupled and / or synchronized drive instances where the pathological activity sensor 3 via the measured amplitude to be decoupled corresponding to the neuron population. 幅度这样ー来就代表了病理性特征。 Such that the magnitude ー come on behalf of the pathological features. 然后能够经由信号最大值的确定或者经由信号量平均值或者用带通滤波和/或用希耳伯特变换和/或小波分析来估计幅度。 It can then be determined or an average or conversion bandpass filtering and / or a Hilbert and / or wavelet analysis to estimate the amount of the maximum amplitude of the signal via the signal via. 特别优选地使用前两个变体（信号最大值的确定或信号量平均值的确定），因为借助于希耳伯特变换和/或小波分析的幅度计算意味着显然更高的计算工作量，并且它们的准确度取决于算法參数的正确选择。 Particularly preferably used the first two variants (or determining the amount of signal determined average maximum signal), since the amplitude by means of a Hilbert transformation and / or wavelet analysis calculated mean clearly higher computational effort, and their accuracy depends on the correct choice of algorithm parameters.
[0171] b)如果除了疾病特定活动之外，经由传感器3还测量例如来自其他神经元群体的非疾病特定活动，则神经活动不能直接应用于估计病理性特征的实例。 [0171] b) If in addition to the disease-specific activity, e.g. measuring sensor 3 further activity from other non-disease specific neuronal populations through, the neural activity can not be directly applied to the estimation instance pathological features. 由于疾病特定活动典型地在与非疾病特定活动的频率范围不同的频率范围内发生，所以在这种情况下优选地在疾病特定频率范围内估计该活动。 Since the disease-specific activity typically occurs within a frequency range non-disease specific activity of different frequency ranges, it is preferable to estimate the activities within a particular frequency range of disease in this case. 这例如通过频率分析来实行。 This may for example be effected by frequency analysis. 例如，能够确定疾病特定频率范围内的频谱能量。 For example, it is possible to determine the spectral energy within a specific frequency range of diseases. 作为选择，在带通滤波之后，能够通过确定带通滤波信号的最大值或通过确定信号量平均值和/或用希耳伯特变换和/或用小波分析来确定幅度。 Alternatively, after the band-pass filter, it is possible by determining the maximum value of the band-pass filtered signal or by determining the average amount of signal and / or a Hilbert transformation and / or wavelet analysis to determine amplitude.
[0172] 如果预期效果没有实现，換言之如果将要去耦的群体没有充分去耦并从而神经活动的病理性特征没有转移到阈值之下，则慢慢増加激励的最大強度，一直到为了安全的原因而严格预定的最大值，例如5V (例如以每50个周期0. 5V的步长)。 [0172] If the desired effect is not achieved, in other words if the decoupled groups do not fully decoupled and thus the pathological features of neural activity are not transferred to below the threshold, then slowly to increase in the excitation maximum intensity, until for safety reasons strictly predetermined maximum value, for example 5V (e.g. every 50 steps in the cycle 0. 5V). 为了这个目的，根据本发明的装置具有这样的控制系统，其检测神经活动中的变化，并且当神经活动中的变化消失时，朝向上限值适应刺激信号。 For this purpose, the device according to the invention having such a control system, which detects a change in the neural activity, and when a change in the neural activity disappears, toward the upper limit value of a stimulation signal adaptation. 在近似20个成功周期的刺激之后，装置能够开始慢慢地将激励的最大強度（例如以每50个周期0. 5V的步长）校正到较低值，只要刺激结果仍然存在。 After approximately 20 cycles of stimulation successful, the device can begin slowly excitation maximum intensity (e.g. 50 cycles per step 0. 5V) is corrected to a lower value, as long as the stimulus persists result. 在这个过程期间，如上所述地确定刺激結果。 During this process, the results of stimulation is determined as described above. 以这样的方式编程控制系统：它检测神经活动中的变化以及因而的刺激結果。 In such a manner programmed control system: it detects change in the neural activity and thus the result of the stimulation. 以这样的方式在神经活动的10和1000个周期之间的时间尺度上优选地控制最大激励強度：充分地对将要去耦的神经元群体去耦和去同止/J/ o In such a manner on a time scale between 10 and 1000 periods of the neural activity is preferably controlled maximum excitation intensity: sufficiently neuron population to be decoupled to and decoupled with the stop / J / o
[0173] 独立于上面规定的刺激强度值，对将要去耦的神经元群体的合成刺激影响的幅度，在成功的去耦之后，由于根据本发明的装置的刺激机理的部分5中描述的特性而被自动地最小化。 Amplitude [0173] independently of the above-specified stimulation intensity values, the influence of the neuron population to be decoupled synthesis stimulation after a successful decoupling, since the characteristic portion 5 stimulation mechanism apparatus of the present invention is described with respect to It is automatically minimized.
[0174] 7. 3用于电极2没有位于将要去耦的神经元群体内的情况的刺激參数 [0174] 7.3 for the case where the electrode 2 is not located within the neuron population to be decoupled stimulation parameters
[0175] 如描述的电极2没有位于将要去耦的神经元群体内的情况下那样，经由如部分4. I所述的间接刺激影响将要去耦的神经元群体。 [0175] The electrode 2 is not located described above, such as indirect via stimulation on the portion to be decoupled 4. I neuron population in the case of the neuron population to be decoupled. 由于在间接刺激的情况下，一方面刺激目标群体和另ー方面将要去耦的群体之间的传导时间能够在每个情况下都具有不同的量级，所以在执行去耦刺激之前首先測量各个传导时间。 Since in the case of indirect stimulation, on the one hand stimulate the target groups and other aspects will ー conduction time between decoupled groups to have a different magnitude in each case, the respective first measured prior to performing the decoupling stimulation conduction time. 为了这个目的，经由刺激电极2施加激励，并且经由置于将要去耦的神经元群体内的传感器3測量对该激励的响应。 For this purpose, the excitation is applied via the stimulation electrode 2, and 3 via a measuring sensor disposed within the neuron population to be decoupled in response to the excitation. 这被执行L次，其中L典型地为一直到例如200的小整数。 This is performed L times, where L is typically a small integer, for example, up to 200. 由此以以下方式优选地估计平均传导时间： Thereby estimating the average conduction time is preferably in the following manner:
[0176] 经由电极2的激励应用的开始和对激励的响应或对激励的响应的量的第一最大值之间的持续时间T (k)，为每个単独的激励应用确定。 [0176] and determined by the start of the excitation electrode 2 for the application or in response to a time duration between the first maximum amount of excitation in response to excitation of the T (k) for each excitation radiolabeling separate application. 在T (k)中，指数k代表第k个施加的激励。 In the T (k), the index k represents the k-th excitation applied. 由此，根据以下的公式1，对于经由其间接施加刺激的刺激电极2，然后分开地确定激励开始和激励响应之间的平均持续时间： Thus, 1, 2, and then determining the average time duration between the excitation and response to excitation start stimulation electrode via which the indirect stimulation is applied separately according to the following formula:
[0177] T=-Ytw [0177] T = -Ytw
L k=i L k = i
[0178]公式 I [0178] Formula I
[0179] 其中L是经由刺激电极2施加的刺激的数目。 [0179] where L is the number of the stimulation electrode 2 via the stimulation applied.
[0180] 对于刺激，以以下方式考虑以这种方式确定的传导时间T ： [0180] For stimulation, considered in this manner is determined in the following manner conduction time T:
[0181] 如果在直接刺激将要去耦的神经元群体的情况下，则会经由刺激电极2以时间延迟t施加激励，在间接刺激的情况下，经由刺激电极2以时间延迟tY给予激励，其中t必须大于て，其能够根据部分7. 2. 2实现。 [0181] If the direct stimulation of the neuron population to be decoupled case, the excitation occurs via the stimulation electrode 2 is applied to the delay time t, in the case of indirect stimulation via the stimulation electrode 2 with a time delay given excitation tY, wherein te must be greater than t, which enables a partial 7. 2.2.
[0182] 如上所述地考虑传导时间Y，如部分7. I和7. 2中描述的那样完全类似地执行刺激开始时刺激參数的确定和刺激期间的控制机制。 [0182] Consider as described above transit time Y, such as the control portion 7. I and entirely similar mechanism determines that stimulation is performed at the beginning of stimulation parameters as described in 7.2 and during stimulation.
[0183] 例子和装置的其他实施例 [0183] Other embodiments and examples of apparatus
[0184] 8. I 例子 [0184] 8. I Examples
[0185] 例如，经由电极能够递送以下激励： [0185] For example, via the excitation electrodes can deliver the following:
[0186] I.经由电极，施加刺激激励，其由两个成分组成：反馈刺激信号，亦即处理过的神经活动，其中刺激信号时间偏移T/2，其中T是将要去耦的神经元群体的振荡平均周期。 [0186] I. via the electrodes, stimulation stimulus is applied, which consists of two components: a feedback stimulation signal, i.e. the treated neural activity, wherein the stimulation signal time offset T / 2, where T is the neurons to be decoupled the average period of oscillation groups. 非时间延迟处理的神经活动被添加到这个信号上。 Time delay processing of non-neural activity is added to this signal. 它们一起形成刺激激励，见图2。 Which together form the stimulation stimulus, shown in Figure 2.
[0187] 2.经由电极，施加信号，其由三个成分组成：处理过并且非时间延迟的神经活动被平方并乘以时间延迟T/2的且处理过的神经活动，其中T是驱动神经元群体的节律周期，见图3。 [0187] 2 via the electrodes, a signal is applied, which consists of three components: treated and non-time-delay neural activity is squared and multiplied by the time delay and the treated T / 2 neural activity, where T is the driving nerve rhythm cycle yuan groups, shown in Figure 3.
[0188] 刺激对将要去耦的群体的影响在测量的神经活动的幅度減少方面变得明显，见图2a和3a，其中神经元的激发模式显然不同于病理性状态下的激发模式，见图2b和3b。 [0188] stimulation on the population to be decoupled to reduce the amplitude of the neural activity in terms of the measured apparent from Figure 2a and 3a, wherein the neuronal excitation model is clearly different from the excitation mode of the pathological state, see FIG. 2b and 3b. 在将要去耦的神经元群体的同步的程度中也反映了这种刺激影响，见图2c和3c，其表示了将要去耦的群体的去同步正在发生的证实。 The degree of synchronization in the neuron population to be decoupled also reflects the impact of this stimulus, see Fig. 2c and 3c, which represents confirmed to be decoupled to synchronize groups taking place. 在这个过程中，合成刺激影响、亦即耦合与刺激之和的幅度，由于部分5中描述的刺激信号的自调节的需求控制而自动减少并最小化，见图2d和3d。 In this process, the stimulation on the synthesis, i.e. the coupling and the amplitude of the stimulation, because self-regulating demand stimulation signal described in the section 5 is automatically controlled to reduce and minimize, Figure 2d and 3d. 进而，在刺激期间对神经元的固有动态没有影响，其证实神经元群体的固有频率分布在图2e和3e中。 Further, during the stimulation has no effect on the inherent dynamics of neurons, which confirmed that the natural frequency of the neuron population distribution of figure 2e and 3e. 固有频率被理解为没有交互作用并且没有刺激的状态下的神经元的频率。 Not to be understood as the natural frequency and the frequency of interaction of neurons in a state without stimulation. 这证实将要去耦的神经元群体的最佳去耦和去同步由于根据本发明的刺激已发生,并且该群体已因而返回到其正常功能状态，其允许预期疾病相关症状的显著減少。 This confirms that the best decoupling of the neuron population to be decoupled and stimulation according to the present invention because the synchronization has occurred, and thus the group has returned to its normal functional state, which is expected to allow the disease-related symptoms significantly reduced.
[0189] 例如，部分6中描述的激励应用的三种不同控制机制用于刺激，借助于此，优选地使需求控制的、并因而能量节省且和缓的刺激（避免副作用）成为可能，如部分7所述： [0189] For example, three different control mechanisms excitation part 6 described in the application for stimulation, by means of which, preferably that the control requirements, and therefore energy savings and gentle stimulation (to avoid side-effects) as possible, as part of 7:
[0190] I.持久激励应用：持久地、优选地以刺激周期适应的方式施加刺激。 [0190] I. Application of persistent excitation: permanently, preferably in a manner adapted to the stimulus is applied stimulation period. 直接地在刺激施加之后，将要去耦的神经元群体的去耦和去同步发生。 After the stimulus is applied directly, the decoupling of the neuron population to be decoupled and the desynchronization occurs. 这使测量的神经活动的幅度最小化。 This makes measuring the amplitude of the neural activity is minimized. 与此同时，刺激对将要去耦的群体的合成影响的幅度，由于部分5中描述的自调节的需求控制的机制而被最小化。 At the same time, stimulating effects on the synthesis of a population to be decoupled amplitude, since a self-regulating mechanism portion 5 needs described control is minimized. 在已断开刺激之后，再同步由于群体之间病理性相互作用而可能在短时间之后发生。 After disconnected stimulation, resynchronization due to the pathological interaction between groups that may occur after a short time.
[0191] 2.重复激励应用，优选地具有需求控制的激励強度：重复地施加刺激。 [0191] 2. Repeat excitation applied, preferably having a demand-controlled excitation intensity: repeatedly applied stimulus. 在这个过程中，激励的强度适合于神经元群体的同步的强度：耦合和/或同步越强，协同的激励将越強。 In this process, the intensity of the excitation intensity is adapted to synchronize the neuron population: coupling and / or synchronizing the stronger, the stronger the synergistic excitation.
[0192] 在这个变体中，T/2而不是T/2能够优选地选择作为时间延迟，其中T是没有刺激的节律周期，而T则是通过刺激在节律上强加的周期。 [0192] In this variant, T / 2 instead of T / 2 can be preferably selected as a time delay, where T is the period of the rhythm without stimulation, and T is the rhythm imposed by the stimulation period. 換言之：I/ T是用其施加单独激励的刺激信号的频率。 In other words: I / T is the frequency of the stimulation signal by applying a separate excitation. 结果，仅有的决定性刺激參数被强加到系统上：代替作为精心设计的校准的部分以适当的方式确定这个參数，它由刺激指示。 As a result, the only decisive stimulation parameters are imposed on the system: in place as part of the calibration designed to determine this parameter in a suitable manner, it is indicated by a stimulus. 另外，这种形式的需求控制的刺激利用了下述环境：受影响区域中的神经元具有用于周期性激发或爆发（动作电位脉冲有节律的产生）的（病理性）趋势。 Further, this form of demand-controlled environment stimulated using the following: by neurons in a region having a periodic outbreaks or excitation (generation of action potentials with a pulse rhythm) of (pathological) trend. 因为这个原因，关于强加的频率能够实现将要去耦的神经元群体的神经活动的传输（entrainment)。 For this reason, the frequency imposed on enables the transmission of neural activity of the neuron population to be decoupled (entrainment). 3.刺激激励的需求控制的激励应用（亦即刺激的开始和结束时间的需求控制的选择）：如果神经细胞群体的同步超过阈值，则经由电极递送下ー个激励，如部分6. 3所述。 3. Application of excitation stimulation stimulus control demand (demand i.e. start and end times of the selection control stimulus): If synchronization neural cell population exceeds a threshold value, the lower electrode via the excitation ー delivery, such as 6.3 part above.
[0193] 在经由上面的例子描述的全部三种控制方法中，部分5中描述的自调节的需求控制使输入到将要去耦的群体中的能量的最小化成为必要。 [0193] In all three control methods described by the example above, self-regulating requirements described in section 5 of the control input to the population to be decoupled energy minimization becomes necessary. 在这个过程中，通过测量将要去耦的神经元群体和/或驱动神经元群体或紧密连接到其的别的神经细胞群体中的神经细胞群体的频率，能够优选地适应仅有的重要刺激參数，即刺激周期T以及因而的时间延迟。 In this process, the neuron population to be decoupled and / or the driving neuron population or in close connection to the frequency by measuring the population of other neurons in the neural cell population thereof can be preferably adapted to the only significant stimulation parameters number, i.e. the stimulation period T and thus the time delay.
[0194] 存在例如通过在从电极的末端的不同距离处安置刺激触点将若干刺激电极组合在将要植入的ー个刺激电极中的可能性。 [0194] In the present example, by stimulating the contacts arranged at different distances from the tip of the electrode several possibilities to be combined in a stimulation electrode implanted ー stimulation electrodes. 这使得可以实现尽可能全面的将要去耦的区域的刺激。 This makes it possible to stimulate the overall area to be decoupled can be achieved.
[0195] 8. 2装置的其他实施例 [0195] Other embodiments of the apparatus of Example 8.2
[0196] 根据本发明的装置还能够用于对病理性同步的神经元群体去同步。 [0196] Synchronization of the neuron population to pathological synchronizing apparatus according to the present invention can also be used. 在根据本发明的装置的这个实施例中，病理性同步的神经元群体，例如将要去同步的驱动神经元群体，借助于具有根据本发明的反馈刺激信号的刺激而去同歩。 In accordance with this embodiment of the device according to the present invention, synchronization pathological neuronal populations, such as going to the neuron population driven synchronously, by means of a feedback stimulus away with the stimulation signal according ho the present invention. 上面描述的装置的特性和用于将要去耦的神经元群体去耦的刺激方法同样适用于装置的这个实施例，其具有下述修改：在将要去同步的神经元群体内施加刺激。 The above described characteristics of the apparatus and method for stimulating the neuron population to be decoupled decoupling is equally applicable to this embodiment of the device, which has the following modifications: stimulation is applied in the neuron population to be desynchronized. [0197] 如果目标是去同步，则这能够借助于根据部分4. I的刺激电极2的布置来实现。 [0197] If the goal is to synchronize, then this can be achieved according to the arrangement portion 4. I 2 by means of the stimulation electrode. 传感器3的直接和间接布置也是可能的。 Direct and indirect sensor arrangement 3 are also possible. 在这种情况下，必须以这样的方式布置传感器3 ：将要去同步的区域的神经活动的检测是可能的。 In this case, the sensor must be arranged in such a way 3: go to the neural activity detected synchronization area are possible. 这种布置的细节对应于部分4. 2中描述的细节，其中现在测量的是将要去同步的活动。 Details of this arrangement corresponds to the section 4.2 of the detailed description, which is now measured the activities to be desynchronized. 根据部分3直接和/或间接地測量并处理将要去同步的神经元群体的病理性同步活动。 The measurement portion 3 directly and indirectly / or treatment and pathological neuron population to be desynchronized synchronous activity. 这生成刺激信号，其用作用于刺激激励的基础。 This produces a stimulation signal, which is used as a basis to stimulate excitation. 借助于刺激电极将生成的刺激激励施加到将要去同步的区域，以便根据部分3和4. I发生将要去同步的群体的直接或间接刺激,并且根据本发明去同步驱动群体并抑制病理性症状。 The stimulation electrode by means of stimulating excitation is applied to the area to be desynchronized, to directly or indirectly stimulate population to be desynchronized depending portion 3 and 4. I, and to drive the synchronous group of the present invention and inhibit pathological symptoms . 如果存在，则到被驱动神经元群体的驱动耦合也由于驱动群体的去同步、亦即由于驱动神经元群体的去同步而被自动地去耦，被驱动神经元群体的病理性驱动消失。 If present, the drive to the drive coupling is also due to the neuron population to population synchronous drive, i.e. the drive of the neuron population to be desynchronized automatically decoupled pathological neuron population driven drive away. 由于刺激信号与将要去同步的神经元群体的神经活动的关系，刺激对将要去同步的群体的合成影响的幅度，亦即当前情况下刺激信号的幅度（见部分2)，如部分5所述被自动最小化。 Since the relationship between the stimulation signal to be desynchronized neural activity of the neuron population stimulated biosynthesis in a population to be desynchronized amplitude, i.e. the amplitude of the stimulation signal in the present case (see part 2), as described in Section 5 It is automatically minimized.
[0198] 根据部分4的适合于刺激目标的电极和传感器的布置、根据部分6的控制激励应用的全部三种控制方法、以及根据部分7的參数的校准和适应，同样能够用于描述的根据本发明的装置的实施例。 [0198] The sensor arrangement is adapted to stimulate the target electrode and the portion 4, all three control method in accordance with section 6 of stimulus application, and based on the calibration parameter and the adaptation part 7, it can be used to describe the same embodiment of the device according to the invention.
[0199] 装置还能够用于去耦由非同步病理性神经元群体驱动的神经元群体。 [0199] means for decoupling can also be driven by the neuron population asynchronous pathological neuron population. 进而，装置能够用于去耦这样的群体，其由病理性活动驱动，并且在去耦状态下自身展示非病理性同步活动。 Furthermore, means for decoupling can be such a group, which is driven by a pathological activity, and show their non-pathological synchronous activity in the decoupled state. 在这种情况下，电极和传感器的布置与部分4中描述的布置相同。 In this case, the electrode arrangement and the sensor arrangement portion 4 with the same as described. 同样根据部分3实现神经活动的检测和处理。 And achieve the same detection processing of the neural activity in accordance with section 3.
[0200] 进而，装置能够用于消除或抑制非病理性区域的耦合。 [0200] Further, the device can be coupled for eliminating or suppressing non-pathological area. 这能够例如用在神经元群体的交互作用的检查中。 This interaction can be for example in the inspection of the neuron population. 神经活动的检测和处理以及电极和传感器的布置在这里根据部分3和4发生。 Detection and processing, and arrangement of electrodes and sensors neural activity here depending portions 3 and 4.
[0201] 如果像引言中提到的那样，对于去耦病理性活动双侧刺激是必要的，则优选地用两个单独装置双侧地或者用根据本发明的ー个装置，其为了这个目的而设计，能够将信号前转到至少两个刺激电极，来施加刺激。 [0201] If so, as mentioned in the introduction, is necessary for decoupling the pathological activity bilateral stimulation, it is preferable to use two separate devices or bilaterally with a ー apparatus according to the invention, which for this purpose design, can be pre-signal to the at least two stimulation electrodes, stimulation is applied.
[0202] 优点 [0202] advantages
[0203] 与例如DE 103 18 071. 0_33“用于去同步神经大脑活动的装置”的现有装置相比，根据本发明的装置具有若干优点： [0203] Compared with e.g. 10318 0_33 071. "means for desynchronization of neural brain activity" in the conventional device DE, it has several advantages according to the present invention:
[0204] I.根据本发明的装置的主要优点在干，病理性激励，亦即反馈刺激信号，換言之即将要去耦的神经元群体和/或将要去同步的神经元群体的測量过并处理过的神经活动，用于刺激。 [0204] I. The major advantages of the device according to the present invention when dry, pathological excitation, i.e. feedback stimulation signal, in other words is about the neuron population to be decoupled and measuring neuron population and / or to be desynchronized and treated by off neural activity for stimulation. 结果，部分5中描述的刺激信号的自调节的需求控制发生，其使输入到将要去耦的神经元群体或将要去同步的神经元群体中的能量最小化，并且导致轻微的副作用。 As a result, self-regulating demand stimulation signal described in section 5 controls occurs, the energy input to the neuron population to be decoupled or the neuron population to be desynchronized is minimized, and leads to minor side effects.
[0205] 2.由于根据部分5的自调节的刺激信号，所以根据本发明的装置的操作节约能量，因为既能量节约信号由于需求控制的刺激信号而用于刺激，又在刺激控制所需的根据本发明的控制装置中能够预期能量节约。 [0205] 2. Due to the self-regulating stimulation signals section 5, the energy saving operation of the device according to the present invention, since both the energy savings due to the stimulation signal and the control signal requirements for stimulation, and the desired stimulus control the control apparatus according to the present invention, the energy saving can be expected. 结果，令患者筋疲力尽的必要电池更换之间的间隔能够更长。 As a result, the interval between necessary so that patients exhausted battery replacement can be longer. [0206] 3.具有需求控制的刺激強度的重复或持久应用的实施例尤其有利，因为在这种方法中不需要检测阈值。 Repeated or prolonged application of an embodiment is particularly advantageous [0206] 3 having a demand-controlled stimulus intensity, because in this method does not require detection threshold. 结果，能够借助于简单得多的算法实行这个实施例。 As a result, by means of much simpler algorithms to implement this embodiment. 相应地，它们的软件或硬件实现更少复杂。 Accordingly, they are less complex hardware or software.
[0207] 4.在具有需求控制的激励強度的持久和重复刺激以及将要去耦的神经元群体或将要去同步的神经元群体的直接刺激的情况下，校准不是必要的，亦即没有必要执行其中刺激參数被系统性地改变的一系列测试刺激，这导致減少的校准持续时间。 [0207] 4. In the case of a demand-controlled excitation intensity and persistence of repetitive stimulation and direct stimulation of the neuron population to be decoupled or the neuron population to be desynchronized, the calibration is not necessary, i.e., not necessary to perform wherein the stimulation parameters are systematically varied series of test stimuli, which results in reduction of duration of the calibration.
[0208] 5.与诸如强度、刺激周期和时间延迟之类的參数的估计相比，关于大的优点总的就是根据本发明的装置的一般公差和耐久性。 [0208] 5. Compared with the estimated such as strength, stimulation period, and time delay parameters and the like, and the overall durability of the general tolerance is about great advantage of the apparatus according to the invention.
[0209] 6.通过仅使用一个电极，手术复杂性以及因而的手术期间并发症的风险对于患者显著降低。 [0209] 6. By using only one electrode, operation complexity and thus the risk of complications during surgery for the patient significantly reduced. 结果，根据本发明的装置提供了和缓得多的激励应用。 A result, a much more gentle stimulus application device according to the invention.
[0210] 7.由于将要去耦的区域优选地位于大脑表面附近，例如运动皮质中，所以接近将要刺激的区域容易得多并且具有更少的风险，例如没有刺激电极的深度植入。 [0210] 7. Since the decoupled region is preferably located near the surface of the brain, for example, the motor cortex, the area close to be stimulated much easier and with less risk of, for example, did not stimulate the implanted depth electrode.
[0211] 8.装置还能够用于去耦非病理性活动，并且这样ー来就为检查大脑中神经群体的交互作用提供了新颖且重要的可能性。 [0211] 8. The device can also be used for decoupling non-pathological activities, and thus provides a novel ー be important possibilities for inspection and interaction of the brain neural population.
[0212] 没有耗时的校准以及甚至具有相对大的频率波动的效果稳定性——尤其是在控制激励应用的方法I中（持久刺激，见部分6. I)——具有重要的后果。 [0212] No time-consuming calibration and even has an effect of frequency fluctuations in a relatively large stability - especially in the control of the stimulus application process I (lasting stimulation, see section 6. The I) - has important consequences.
[0213] I.在电极的置換期间甚至在外科手术进行时就能立刻检查刺激結果。 [0213] I. even able to immediately check the results in the stimulation intraoperatively during replacement of the electrode. 结果，能够明显改善适当目标点的发现。 As a result, significant improvement was found appropriate target. 以前的需求控制方法需要持续长于每电极30分钟的校准。 Previous demand control method requires calibration duration longer than 30 minutes per electrode. 这不能在外科手术进行时执行，并且不是患者所期待的（其未被麻酔）。 This can not be performed intraoperatively, and the patient is not expected (it is not Anesthesiology).
[0214] 2.新的方法还能够用在神经或精神疾病中，其中病理性节律具有很大波动的频率。 [0214] 2. The new method can also be used in neurological or psychiatric disorders in which pathologic rhythm having a great frequency fluctuation. 特别地，新的方法还能够用于去耦间歇（亦即短时期）发生的节律。 In particular, the new method can also be used for decoupling the intermittent rhythm (i.e. a short period) occurs. 结果是，新的刺激方法能够用在多得多的疾病中，尤其是还能够用于癫痫的情況。 As a result, a new stimulation methods can be used in many more diseases, in particular, it can also be used in the case of epilepsy.
[0215] 使用根据本发明的装置，用新的刺激方法通过去耦适当的大脑区域能够治疗以下疾病或症状。 [0215] use of the device according to the invention, with new stimuli decoupling method capable of treating the appropriate areas of the brain disease or symptoms.
[0216] 在所有的神经或精神疾病中，其中病理性神经同步扮演了与疾病特定症状的实例相关的角色，例如：帕金森病、特发性震颤、肌张力障碍、強迫症疾病、多发性硬化中的震颤、作为中风或其他组织损伤（例如肿瘤组织损伤，例如在丘脑和/或基底神经节的区域中）的后果的震颤、舞蹈手足徐动症以及癫痫，这种列举并不规定为限制性的。 [0216] In all neurological or psychiatric disorders in which pathological neural synchronization plays a role instance associated with disease-specific symptoms, such as: Parkinson's disease, essential tremor, dystonia, obsessive-compulsive disorder disease, multiple sclerosis tremors, as a stroke or other tissue damage (e.g. tumor tissue damage, for example in the area of ​​the thalamus and / or basal ganglia) tremor consequences, dance athetosis and epilepsy, this list is not defined as restrictive.
[0217] 在当前使用的标准方法中，连续高频的刺激，使用以下目标区域，例如： [0217] In the standard methods currently used, continuous high-frequency stimulation, the following target area, for example:
[0218] 帕金森病情况下的丘脑下神经核或震颤支配的帕金森病情况下的丘脑，例如丘脑中间腹侧核。 [0218] Parkinson's disease hypothalamus of nuclear or hypothalamic nerve dominant tremor in Parkinson's disease, for example thalamic ventral intermediate nucleus.
[0219] 在特发性震颤的情况下，丘脑，例如丘脑中间腹侧核。 [0219] In the case of essential tremor, thalamus, hypothalamus e.g. ventral intermediate nucleus.
[0220] 在肌张カ障碍和舞蹈手足徐动症的情况下，苍白球内部，在癫痫的情况下，丘脑下神经核、小脑、丘脑核心区域，例如丘脑腹侧核或尾状核。 [0220] In the case of muscle disorders and Zhang ka dance athetosis internal globus pallidus, in the case of epilepsy, hypothalamic nucleus, cerebellum, thalamus core areas, such as the thalamus ventral caudate nucleus or nuclei.
[0221] 在強迫症疾病的情况下，内囊或伏隔核。 [0221] In the case where the disease obsessive compulsive disorder, the bladder or the nucleus accumbens.
[0222] 在根据本发明的装置中，例如，能够选择用于各个疾病的上面列举的目标区域和/或与其耦合的区域。 [0222] In the present invention, for example, can be selected for individual diseases listed above target area and / or region coupled thereto. 因为根据本发明的装置或者不需要校准，或者能够非常迅速地执行校准，所以存在下述可能性：作为电极植入的部分测试可替选的目标区域，其中能够甚至更好地改善根据本发明的装置的去耦效果和/或去同步效果。 Because the device according to the invention or no calibration or calibration can be performed very quickly, so there is a possibility: an electrode portion implanted alternative test target area, which can be even more improved according to the invention decoupling effect devices and / or de-synchronization effect. [0223] 本发明还包含控制系统，其如规定的那样控制根据本发明的装置的操作，和装置与控制系统的使用，用于治疗下述疾病：帕金森病、特发性震颤、肌张力障碍、強迫症疾病、舞蹈手足徐动症、多发性硬化中的震颤、作为中风或其他组织损伤（例如肿瘤组织损伤，例如在丘脑和/或基底神经节的区域中）的后果的震颤、以及癫痫。 [0223] The present invention further comprises a control system, such as controlling the use of a predetermined operating device according to the present invention, a control system and apparatus for the treatment of the following diseases: Parkinson's disease, essential tremor, dystonia disorder, obsessive-compulsive disorder disease, choreoathetosis disease, multiple sclerosis tremors, as a stroke or other tissue damage (e.g. tumor tissue damage, for example in the area of ​​the thalamus and / or basal ganglia) consequences tremor, and epilepsy.
[0224] 根据本发明的装置既能够作为植入物用于上述神经和精神疾病的持久治疗，又能够用于外科手术进行时的目标诊断，亦即在外科手术进行时发现用于电极植入的最佳目标点。 [0224] The device of the invention can be used as both an implant for the treatment of persistent neurological and psychiatric disorders described above, but also can be used to target for surgical diagnosis, i.e. be found in the surgical implantation of an electrode the optimal target point.
1. 一种用于去耦和/或去同步神经大脑活动的装置，包括： —至少一个传感器（3)，用于测量至少一个信号，其再现将要去耦的神经元群体和/或将要去同步的神经元群体的活动在时间方面的发展；以及--[合好一个具有至少一个电极表面（2)的电极体； 其特征在于： ——控制系统（4)，其以这样的方式构造：它接收所述传感器（3)的测量信号，并且将所述测量信号作为刺激信号直接馈送到所述电极体中，或者处理所述测量信号，然后将它们作为刺激信号馈送到所述电极体中，其中所述处理包括以下处理步骤中的至少一个：——滤波所述测量信号； ——延迟所述测量信号； ——放大所述测量信号；以及——改变所述测量信号的极性。 An apparatus for decoupling and / or desynchronization of neural brain activity, comprising: - at least one sensor (3), for measuring at least one signal, which reproduces the neuron population to be decoupled and / or going development activities synchronous neuron population in terms of time; and - [Hao electrode body having a surface at least one electrode (2); characterized in that: - the control system (4), which is constructed in such a manner : it receives the sensor (3) of the measurement signal and the measurement signal as a stimulation signal fed directly to the electrode body, or processing the measurement signal, which are then fed as a stimulation signal to the electrode body in which said step of processing includes at least one of: - filtering said measurement signal; - delaying the measurement signal; - amplifying the measuring signal; and - changing the polarity of the measurement signal .
2.如权利要求I所述的装置，其特征在于——控制系统（4)经由所述传感器（3)直接和/或间接地测量将要去耦和/或将要去同步的神经元群体的活动的随时间变化，其中在间接测量的情况下，所述控制系统⑷特别地经由所述传感器⑶中的至少一个测量将要去耦和/或将要去同步的区域所影响的肌肉组的活动的随时间变化，和/或与将要去耦和/或将要去同步的区域相关联的神经元群体的活动的随时间变化。 2. The apparatus according to claim I, characterized in that - the control system (4) / decoupled or measuring the activity and / or a neuron population to be desynchronized directly and indirectly via the sensor (3) It changes with time, which in the case of indirect measurement, the control system ⑷ in particular at least one measurement of the sensor ⑶ via the active groups of muscles being affected decoupled and / or the area to be desynchronized with time, and / or to be decoupled and / populations of neuronal activities associated with the area to be desynchronized or change over time.
3.如权利要求2所述的装置，其特征在于——所述控制系统（4)持久地，或者在时间限制的测量间隔中，测量所述活动的随时间变化，其中所述控制系统（4)在时间限制的测量间隔中，特别地借助于确定性和/或随机和/或组合的随机/确定性的算法控制所述限制的测量间隔的持续时间和/或间隔，并且/或者——所述控制系统（4)存储所述测量信号。 3. The apparatus according to claim 2, characterized in that - the control system (4) permanently, or the time limit of the measurement interval, the measurement of the activity changes with time, wherein said control system ( 4) measurement interval time limit, in particular by means of the duration of the measurement interval deterministic and / or random, and / or a combination of control algorithms random / deterministic the restriction and / or spacing, and / or - (4) storing the measurement signal of the control system -.
4.如权利要求I至3中之一所述的装置，其特征在于——所述控制系统（4)包含需求控制。 4. The apparatus of claim I according to one of the 3, characterized in that - the control system (4) comprises a demand control.
5.如权利要求4所述的装置，其特征在于——所述控制系统（4)使用所述测量信号和/或所述刺激信号用于所述需求控制，并且/或者——所述控制系统（4)检测所述测量和/或刺激信号中的病理性特征，并且/或者——所述控制系统（4)使用所述测量和/或刺激信号的幅度用于所述需求控制，并且/或者——所述控制系统（4)通过使用信号自身和/或信号的绝对值和/或在疾病特定频率范围内带通滤波的信号和/或在疾病特定频率范围内带通滤波的信号的绝对值和/或希耳伯特变换和/或小波分析所确定的瞬时幅度来估计所述测量和/或刺激信号的幅度，并且/或者——所述控制系统⑷当在所述测量和/或刺激信号中检测病理性特征时，施加刺激激励,并且/或者——所述控制系统（4)通过检测所述测量和/或刺激信号的幅度阈值的越界来检测病理性特征，并且/或者——所述 5. The apparatus according to claim 4, characterized in that - the control system (4) using the measurement signal and / or said demand control signal for the stimulation, and / or - the control and / or wherein the stimulation signal in rational system disease (4) detecting the measurement, and / or - the control system (4) using the measurements and / or amplitude of the stimulation signal for said demand control, and / or - the control system (4) by using the signal itself and / or the absolute value signal and / or disease-specific frequency range within the band-pass filtered signal and / or disease-specific frequency range within the band-pass filtered signal absolute value and / or a Hilbert transformation and / or wavelet analysis of the determined instantaneous amplitude estimating the measured and / or amplitude of the stimulation signal, and / or - the control system and the measurement when ⑷ / or stimulation signal upon detection of disease features rational, stimulation stimulus is applied, and / or - the control system (4) is detected by detecting the disease rational characterized in measuring and / or bounds stimulation amplitude threshold signal, and / or - the 控制系统（4)通过检测在疾病特定频率范围内带通滤波的測量信号和/或刺激信号的幅度阈值的越界来检测病理性特征，并且/或者——所述控制系统（4)为了检测病理性特征，在滑动时间窗ロ中将所述测量和/或刺激信号的幅度与所述阈值相比较。 The control system (4) by detecting the disease in a specific frequency range of the bandpass filtered measurement signal and / or cross-border stimulation amplitude threshold signal to detect characteristics rational disease, and / or - the control system (4) in order to detect pathological characteristics, in the sliding time window ro the measured and / or amplitude of the stimulation signal is compared with the threshold value.
6.如权利要求I所述的装置，其中所述装置用于治疗下述疾病：帕金森病、特发性震颤、肌张カ障碍、強迫性疾病、抑郁症和癫痫。 6. The apparatus of claim I, wherein said means for treating the following diseases: Parkinson's disease, essential tremor, muscle tone ka disorder, obsessive compulsive disorder, depression, and epilepsy.
7.如权利要求I所述的装置，其中，所述装置用于为刺激发现目标点。 7. The apparatus of claim I, wherein said means for finding the target point to stimulate.
CN 200580016785 2004-05-27 2005-04-28 Method and device for decoupling and/or desynchronizing neural brain activity CN1956751B (en)
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CN 200580016785 CN1956751B (en) 2004-05-27 2005-04-28 Method and device for decoupling and/or desynchronizing neural brain activity
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JP5425795B2 (en) * 2007-10-29 2014-02-26 ケース ウェスタン リザーブ ユニバーシティＣａｓｅ Ｗｅｓｔｅｒｎ Ｒｅｓｅｒｖｅ Ｕｎｉｖｅｒｓｉｔｙ Initial motion relaxation high frequency nerve block
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CN105138863B (en) * 2015-08-05 2017-02-15 陕西师范大学 Method for inhibiting cluster synchronization of module neural network with coupling time delay
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