这项工作是由国家神经疾病和中风研究所（NINDS）授予＃R01NS075889-01。这项研究是支持部分由院内研究计划的美国国立卫生研究院临床中心。作者的Shahriar伊克巴尔和涌天，他也感谢协助数据收集。 APDM公司（波特兰，俄勒冈<a href="http://apdm.com" target="_blank">http://apdm.com</a> ）主办的开放式访问的成本，这篇文章发表。

1。主题准备<ol><li>测量对象的身高，体重，并记录他们的年龄。 </li><li>评估主体的首选跑步机的速度，让他们自行调整跑步机的速度，直到舒服。 </li><li>用毡尖笔，标记头的顶点之间的中点的鼻根和INION的的主题。此外，标记10％鼻根的INION距离作为参考对准帽。 </li></ol> 2。头皮脑电图（EEG） <ol><li>脑电图电极连接，所指定使用脑电图主体盖12 10-20国际体系。在头皮上的电极帽，确保妥善安置。 </li><li>关于这个问题的EEG帽放置10％的标记对齐，FP1和FP2电极和锆电极与标记的顶点连线的中点处，从步骤1.3。发现在12个安置的上限的更多细节。硒治愈帽魁梧下巴下面。 </li><li>脑电图电极连接到脑电控制箱。从地面和参比电极，用一个小的注射器注入电解质凝胶在每个电极，直到电极阻抗低于25kΩ每个措施LED返青。在12,13脑电图电极的制备提供进一步的细节。 </li><li>脑电图电极连接到的脑电图无线发射器。固定发射器周围放置的肩膀上的尼龙搭扣的主题和脑电图无线接收器连接到两个32通道放大器。 </li><li>放大器连接到PC主机通过一个USB端口使用一个光纤到USB转换器。 </li><li>将脑电渠道分辨率0.1μV，低截止频率为直流电，和高截止频率为1000赫兹的脑电数据采集软件。 </li></ol> 3。表面肌电图（EMG） <ol><li>准备肌电电极安置8肌肉地点:刮胡子用砂纸打磨，并用异丙醇垫清洁皮肤，磨损。准备的网站上放置电极，并连接肌电图数据记录单元。肌电接地电极放在左或右手腕上，并连接到数据记录单元。 </li></ol> 4。动作捕捉<ol><li>同步MARG传感器同时停靠根据制造商的说明。 </li><li>删除MARG传感器和地方使用Velcro紧固带或双面胶带，在表2中的位置上的主体。 </li></ol> 5。环境准备<ol><li>准备跑步机带在皮带上的对角线（从水平方向45°）。将连接到一台摄像机在跑步机前约1米的电视监视器上。带一张纸，直径为2英寸的电视上的黑色圆圈。 </li><li>设置步行舞台上放置5台红外接近传感器，锥，和电视小号位于图3中的C适度化。 </li></ol> 6。跑步机<ol><li>主题上升到跑步机上。安装安全带。 </li><li>数据收集之前，检查脑电图和肌电图信号来验证正确放置电极，电极连接和数据传输。 </li><li>运行C + +控制台应用开始数据收集。按下手动触发按钮启动肌电图记录和音频提示（蜂鸣声）开始实验。 </li><li>主题保持在安静的姿态，持续30秒。 </li><li>单键触发按钮30秒后开始步行，跑步机慢慢加速到预先选定的主体的速度。 </li><li>走5分钟的主题。 </li><li>在5分钟结束时，将触发按钮开始慢慢停止跑步机步行至站过渡。停止后的主题仍然站在30秒。按&#39;Q&#39;按钮停止数据采集吨里亚尔和保存数据。 </li><li>重复步骤6.2-6.7为所有三个跑步机条件: </li><li>跑步机，一边走一边看着黑点的距离。 </li><li>跑步机上行走，而电视监视器上观察自己的两条腿运动。 </li><li>跑步机上行走，同时利用视频反馈，以避免在跑步机上的对角线（模拟认知负荷6）。 </li></ol> 7。竞技场步行（1） <ol><li>位置须在舞台上走循环（ 图3）的开始。 </li><li>开始数据收集在6.2-6.4。 </li><li>按下触发按钮，开始行走。在当时的触发器的出现，在第一方向的箭头（→，←，↑）对面的主题在屏幕上（ 图3）显示。如果→或←被观察到的，对象离开视锥细胞的入口组，在这个方向旋转90°，完成循环，并返回到入口锥。如果与阿联观察ŗ;，主题继续直出入口处锥和手动触发和方向箭头（→或←）当主体到达前约2米的红外线传感器。所得款项须通过第一套红外传感器，然后作出相应的90°转向完成循环，返回入口锥。 （在行走过程中，实验者遵循主题在距离约3-5米双轮车与​​主机PC上，以提高无线信号的质量。） </li><li>须继续走，当他/她完成一个单一的循环后，到达入口锥。 7.3序列是重复的随机排序的箭头，直到3个回路已经完成每个初始箭头（→，←，↑）。 </li><li>满足条件7.4后，按下手动触发按钮，当目标到达入口锥信号过渡到站立。主题静静地矗立，持续30秒，然后按&#39;Q&#39;按钮，在主机PC上数据收集终止。 </li></ol> 8。竞技场步行（2） <ol><li>重新排列的舞台上走五套红外传感器被定位在一个半圈的主体的前部（ 图4），使过程。 </li><li>开始数据收集与以前的试验（7.1-7.2）。 </li><li>竞技场走我相似，手动触发，开始步行。在触发时，一个星方向箭头（←，→， <img src="/files/ftp_upload/50602/50602larr.jpg" alt="左箭头" fo:src="/files/ftp_upload/50602/50602larrhighres.jpg" /> ， <img src="/files/ftp_upload/50602/50602rarr.jpg" alt="右箭头" fo:src="/files/ftp_upload/50602/50602rarrhighres.jpg" />或↑）被显示在屏幕上。每个箭头对应于一组红外传感器的位置周围的舞台上（ 图4）。 </li><li>受观察屏幕上的箭头和WALKS红外传感器，使U形转弯绕锥以外的传感器，通过传感器的两倍（ 图4）的对应的一组。后U形转弯，并可返回到起点，继续步行。 </li><li> ，随机排序的箭头，直到重复序列8.3-8.4，已完成3个回路，每个方向箭头。 </li><li>满足条件8.6后，按下手动触发按钮，当主体达到起点的信号过渡到站立。完整的数据收集在7.5。 </li></ol> 9。坐站<ol><li>身后的椅子上的主题定位，数据采集，并开始在6.2-6.3。静静地矗立在开始收集数据，持续15秒的主题。 </li><li> 15秒后，按下手动触发按钮。听完提示主题转换，从站到坐的姿势，坐姿，直到下一个音频提示（按下按钮）。 </li><li&gt;等待一个随机的时间间隔（5-15秒），然后按手动触发给予提示坐站过渡。站立姿势保持，直到下一个音频提示。 </li><li>重复9.2-9.3，直到10个完整的站坐，坐姿到站立演习完成后，静静地矗立在15秒的主题。然后按&#39;Q&#39;键，终止数据收集。 </li><li>重复的立场坐协议（9.1-9.4）， 自我发起的独立坐下来，坐 ​​，站过渡。的主题，而不是给一个触发过渡，让主体开始转移，直到拥有自己的每个动作完成10。 </li></ol> 10。走廊行走<ol><li>在1/8英里，直走廊中间位置的主体和数据收集车。开始数据收集与跑步机上行走实验（6.2-6.4）。在最初的30秒休息期间，手动触发，开始行走。 </li><li> subjeCT连续走5分钟。当主体达到10米之内的走廊末端，他/她的自我启动掉头，继续走在相反的方向。 </li><li>在5分钟结束时，推手动触发按钮，停止走。主体静静地矗立，持续30秒，而直视前方。按&#39;Q&#39;键终止数据收集。 </li><li>开始第二个走廊实验在10.1。 </li><li>行走（20-40秒）后，一个随机时间间隔，给手动触发和音频提示的主题停止行走。 </li><li>的主题仍然站在总之，随机持续时间（5-15秒）。 </li><li>按下手动触发按钮，有主题的简历行走。 </li><li>重复步骤10.5-10.7，直到停止启动10个循环是否齐全; 10.3终止数据收集。 </li></ol>

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这里介绍的协议带来了三种数据收集系统，同时记录大脑活动，肌肉活动，全身运动过程中各种机车的任务。整个协议的完成大约需要3小时，包括1小时的主题准备。被安装在每一个系统，移动，主体。因此，至关重要的是每种新的试验开始前验证EEG和EMG电极的连接。这可以很容易地使用软件包各自的制造商提供的，这使得使用图形界面的PC主机上的实时数据进行审查。数据收集应用程序需要这些软件包在运行，简化验证过程。此外，必须小心，玛格传感器强劲附着在每项试验前的主题。 脑电图和玛格在2.4-2.5 GHz的无线数据传输频谱范围。因为许多其他电子设备都使用这个频段，在实验环境中，重要的是要考虑无线接口的可能性。数据收集的一个重要方面的视线能见度车和主体之间的移动，它提供了无线干扰的鲁棒性。脑电无线接收器和MARG接入点（ 图1）的提供LED来指示连接的保真度。脑电图和玛格传感器PC主机和无线接收器放置在移动的车保持直接的视线，并最大限度地提高无线数据传输为主题的走了过来地面。我们发现，通过移动车保持5米以内的距离没有限制的任务，在任何拍摄对象移动的主体，最好保持强大的数据收集。在C + +应用程序使用多个线程的数据收集提供鲁棒性的无线c中断造成的数据丢失onnection脑电图。如果脑电图连接丢失，玛格及肌电图的数据仍录得，但没有脑电图的数据将可为那些时间点。 MARG传感器提供单位缓冲上面所讨论的，在无线连接的情况下，而肌电图的数据存储在SD卡上，在移动数据记录装置，以防止数据丢失。 脑电图数据收集在行走过程中的一个常见问题是神器存在的信号。从广义上讲，文物可以分成两类:生理来源的文物，包括闪烁，眼球运动，面部肌肉的活动，心脏跳动，机械制品，如运动实验协议执行过程中的电极和/或电缆。神器去除是一个正在进行的研究课题，包括技术独立分量分析15,16和基于通道的模板回归程序17。神器减少和去除是公关的关键步骤数据eprocessing身体运动神经解码。这里介绍的是设置类似于以前的研究中，脑电图电极电缆被捆绑成一个单一的连接器。从这些研究结果表明，由于电缆的晃动或移动的机械制品没有发挥作用，在解码的运动神经活动7,8。这些结果支持由其他研究得出结论，步态相关文物单薄缓慢至温和速度行走17。然而，这个实验活动期间，需要更多的运动的身体比以前的研究，包括坐姿到站立过渡措施，脑电图，超过地面行走，转弯，从而，必须仔细检查原始脑电数据进行识别潜在的从机械制品的污染。尚未广泛使用，但这些潜在的问题可以解决，通过新颖的硬件集成到当前的协议。这样的硬件公司ludes活跃的脑电图电极（在本协议中使用）和弹簧，干脑电图电极，其中有潜力在运动过程中，以改善皮肤的电极接触阻抗18。无线EEG系统，这些技术正在被纳入，这可能会减少运动伪影19的效果。尽管新颖的硬件集成，该协议提供了一个独特的机会，继续开发新的算法为运动和肌电神器的拒绝，因为每一个环节的身体一直仪表16。我们计划研究时间序列相关和频域之间的连贯性脑电图，肌电图，和段运动发展强大的神器抑制范式适用于目前可用的脑电图设置。我们的解码方法对文物7,8的鲁棒性，这些方法将研究在本协议下的更复杂的情况。 记录面的特点肌电图是依赖于很多因素，表面肌电信号的神经战略研究需要解释其代价20。在这个协议中使用的皮肤准备和EMG电极放置的严格的程序而设计的表面上的EMG信号的非生理性因素的影响减到最小。的幅度和频率的肌电图的记录，可通过此协议有关的净电动机单元活动，因此，该记录不应该被解释为所希望的肌肉的神经活动的直接表示。然而，仔细考虑表面肌电信号和更先进的方法来估算神经肌肉驱动肌电信号分解，以确定神经激活的相对变化（ 如通过识别运动单位的放电时间），可以提供有价值的洞察肌肉激活模式20。此外，神经解码的上下文内，尽管大脑的活动侵入性地获取已被证明含有的表面肌电图21的信息，它是目前未知的，，头皮脑电图是否也可用于在行走过程中，除了步态运动学解码下肢肌肉活动。我们预期该协议将允许我们研究降低空间分辨率的非侵入性的脑成像方式是否是足够的隔离个别肌肉的神经活动。 以往的研究表明，利用非侵入性脑电图在跑步机上行走7,8开发的脑机接口（BMI）来恢复行走提供动力来自大脑的信号解码运动学可行性。时域基于振幅调制的Δ-波段的EEG信号的解码方法也被证明是不敏感到人造的元器件7,8。然而，跑步机研究发生在受控环境中，用户的视觉和运动受到限制，从而限制了由于对外界刺激的神经活动的污染。通过成立无线数据记录，该协议允许同步的脑电图，肌电图，动态数据的收集过程中各种运动的任务和环境。集成惯性传感器运动跟踪需要更多的计算和离线处理，提取比动作捕捉系统运动学，和由此产生的措施包含一个小的-但可以接受-的误差幅度，这将不会出现在摄像头为基础的系统22。这些管理的困难是必须建立一个试验性协议，使移动认知电机在变化的环境行为研究。别处讨论10,11的研究可以解决的问题，这样的设置几乎是无限的。在不久的将来，我们的重点将是发展的BMI站在康复的关键问题，并步行后脑损伤和神经病变。一个关键部件，如上面提到的，将是发展新的强大的解码脑机接口的康复机器人系统，可以拒绝使用测量大脑的信号恢复运动生理和机械制品的策略。例如，目前在数据收集过程中与其他人在公共场所进行的走廊行走协议，发展神经解码技术，在自然的环境中，从而提供了一个测试床。使用此协议的其他研究感兴趣的问题包括损伤后急性和慢性两种相比较康复的机器人范式涉及节奏与非节律性步态训练，并在功能恢复的神经活动的研究。

该协议使用三个数据收集系统，同时记录脑电图，肌电图，和全身运动（ 图1，表1）。无线EEG数据收集从64个通道的采样频率为1,000 Hz，而受试者步行。肌电图（EMG）被收集在1000赫兹表面电极置于四个肌肉群:双侧胫骨前肌（TA），腓肠肌（GAST），股二头肌（BF），和股外侧肌（VL）。运动数据被收集在128赫兹，11个无线传感器安装在头部，上身躯干，腰部，手臂，大腿，小腿，脚在行走过程中记录的运动。每个传感器包含一个三轴磁力计，三轴陀螺仪，三轴加速度计（ 即玛格传感器）。 每个系统和数据收集时间由一个单一的PC主机同步。同步是通过使用在一个连续的串行发送一个触发信号人同时访问的所有三个数据系统的通信链路。触发被实现为一个简单的按钮开关。当按钮被按下时，一个触发信号（1）被发送到主机PC，而未按下时，发送一个空信号（0）。按下触发按钮也引出一个0.5秒的音作为被摄对象的音频提示，下面的协议中所描述的。红外（IR）接近传感器5对用于制造过地面步行下述实验过程中触发位置。当IR信号中断的触发信号（1）被发送到PC主机经由无线电频率（RF）与手动触发框中，然后通过串行链接。 一个自定义的C + +应用程序，利用软件开发工具包（SDK），提供每个系统的开发是为了记录和同步数据。代码采用了多线程技术，从每个系统（脑电图，肌电图，MARGs）保存数据的功能都包含在逐张线程idual。 图2中所示的软件算法，当执行应用程序时，数据收集开始和结束时，&#39;q&#39;的键被按下。五个线程应用程序执行时被激活。一个线程（ 图2）监视从串行连接上的触发信号的值（0或1）。初始触发值是零。当收到触发（ 即按钮被按下时，或红外传感器对之间的视线被打破）全局触发变量被设置为1。这些变量保持为1，直到他们是复位内的数据采集线程。 脑电图线程远程访问头皮脑电图数据的实时使用TCP / IP协议。数据被写入到一个文本文件中的行线在相应的采样频率（千赫兹）。全球脑电触发信号被写入到第一列中，而列2-65 64脑电图通道。如果全局的脑电触发信号为1，它是复位到零。数据可继续写入，直到脑电图线程终止。两个独立的线程记录MARG传感器数据。两个线程是必要的，因为11无线玛格传感器的数据传输使用制造商提供的软件，强大的流媒体模式，缓冲各个传感器的数据，以防止数据丢失事件中的无线传输问题。这种缓冲降低实时数据传输:如果一个传感器无法传输数据，对于一个给定的样本，所有的11个传感器保留该时间点在其缓冲区和发送下一个可用的采样点。玛格无线数据传输必然落后脑电图; MARG传感器需要时间缓冲卸载数据到PC主机的数据收集后停止。为了克服这个问题，使用两个线程的MARG数据收集算法（ 图2）。第一个线程填充一个玛格触发缓冲区传感器采样频率（128赫兹）从全球玛格触发变量，而脑电图线程收集的数据。当停止触发缓冲区写入数据收集也将终止。的的MARG线程（ 图2）利用来自传感器的SDK的功能，接收来自传感器的数据，并将其写入到一个文件中相同的方式作为脑电数据。即，第一列是全局的的MARG触发（获得从玛格触发缓冲器）和以下的99列的值，从11 MARG传感器（9的传感器每个MARG单元）获得的值。 MARG线程写入数据，直到时间索引的MARG触发缓冲器等于在该点的线程的执行被终止的脑电数据的最后一个时间索引。 肌电图的数据不同于的脑电图和玛格数据，不记录无线。相反，肌电图的数据记录在SD卡上数据记录单元内。发送信号通过蓝牙连接来启动和停止数据写入到SD卡。开始写作时，第一个接收到手动触发脑电图线程。用脑电数据写入停止&#39;Q&#39;按钮被按下时的线程。 在休斯顿大学的机构审查委员会审议并通过以下协议。所有受试者，阅读并签署一份同意书参与前。

<table border="1">
 <tbody>
 <tr>
 <td>Name</td>
 <td></td>
 <td>Company</td>
 <td>Quantity</td>
 </tr>
 <tr>
 <td>BrainAmp Amplifier</td>
 <td></td>
 <td>Brain Products, Gmbh</td>
 <td>Quantity: 2</td>
 </tr>
 <tr>
 <td>actiCAP EEG cap with 64 electrodes</td>
 <td></td>
 <td>Brain Products, Gmbh</td>
 <td>Quantity:1</td>
 </tr>
 <tr>
 <td>Brainvision MOVE wireless EEG system</td>
 <td></td>
 <td>Brain Products, Gmbh</td>
 <td>Quantity:1</td>
 </tr>
 <tr>
 <td>DataLOG MWX8 EMG data collection unit</td>
 <td></td>
 <td>Biometrics, Ltd.</td>
 <td>Quantity:1</td>
 </tr>
 <tr>
 <td>SX230 EMG electrodes</td>
 <td></td>
 <td>Biometrics, Ltd. </td>
 <td>Quantity:8</td>
 </tr>
 <tr>
 <td>R506 EMG ground electrode</td>
 <td></td>
 <td>Biometrics, Ltd. </td>
 <td>Quantity:1</td>
 </tr>
 <tr>
 <td>Opal movement monitor (MARG sensor)</td>
 <td></td>
 <td>APDM, Inc.</td>
 <td>Quantity:11</td>
 </tr>
 <tr>
 <td>Opal docking station for wireless data streaming</td>
 <td></td>
 <td>APDM, Inc.</td>
 <td>Quantity:2</td>
 </tr>
 <tr>
 <td>Opal wireless access point </td>
 <td></td>
 <td>APDM, Inc. </td>
 <td>Quantity:2</td>
 </tr>
 <tr>
 <td>Infrared Light Barrier Kit MK120</td>
 <td></td>
 <td>Velleman, Inc.</td>
 <td>Quantity:5</td>
 </tr>
 <tr>
 <td>Wixel Programmable USB Wireless Module </td>
 <td></td>
 <td>Pololu, Inc.</td>
 <td>Quantity:6</td>
 </tr>
 <tr>
 <td></td>
 <td></td>
 <td></td>
 <td>Table 1. Equipment</td>
 </tr>
 </tbody>
</table>

simultaneous scalp electroencephalography (eeg), electromyography (emg), and whole-body segmental inertial recording for multi-modal neural decoding

最近的研究支持参与棘上网络控制人类双足行走。这方面的证据包括部分研究，包括我们以前的工作，展示了从头皮脑电图（EEG）解码精度相当高，可以推断，在跑步机上行走的的步态运动学和四肢协调。这些结果提供了推动发展非侵入式脑机接口（BMI）系统，用于修复和/或增强步态康复研究的主要目标。至目前为止，研究活动的脑电图解码步态期间被限制在一个受控的环境中跑步机上行走。然而，要成为实用上可行的BMI系统必须是适用于使用在日常生活中的自发任务，如过地面行走及回转。在这里，我们提出了一种新型的非侵入性的协议，用于收集大脑活动（EEG），肌肉活动（肌电图），和whol电子车身动态数据（头部，躯干，四肢的轨迹）期间都跑步机和对地行走任务。通过收集这些数据在不受控制的环境洞察可以得到解码不受约束步态和表面肌电图从头皮脑电图的可行性。

图5显示了10秒的时间锁定，玛格，脑电图和肌电图的数据记录在跑步机上行走（协议第3节）。请注意，每个玛格传感器实际记录9个信号（三轴磁力计，陀螺仪，加速度计），但只有垂直加速度。 图5中的原始数据包含的文物必须占前预处理过程中分析和神经解码。脑电图文物图5中的例子包括在约8.5秒和低频运动伪影，目前整个眨眼。 图6显示了一个完整的循环（约35秒），地上走在舞台上行走（1）协议。定性分析，数据从地面的舞台上行走任务中含有较多的文物比跑步机上走在转弯过程中，由于附加运动主体的头部和颈部。面部和颅骨的肌肉活动是partic良好的倡议宣传运动尤其明显。在图6中的时间电极（信道在图1中标记为FT和T）。注意EMG信号的活性的增加在跑步机上行走（ 图5）相比，特别是在踝关节的激动剂-拮抗剂对图6还显示事件不理想的无线脑电数据采集，数据处理过程中，必须考虑。紧接的4 个触发之前，脑电图数据显示，扁线，表明一个PC主机和脑电图系统之间的无线传输中断。本节的数据必须从整个数据集（脑电图，玛格，EMG）修剪。 图7显示了一个周期的台阶坐下来，坐 ​​站数据。与其它数据，目前在脑电图移动文物，无论是在过渡期结束，并保持头坐在（或站立）收慢。走廊行走的一个间隔，包括独立行走的一个第二步行到站姿过渡， 如图8所示。注意肌电图和加速度数据的斜坡开始后声音提示，并停止行走。这个斜坡是一致的外观和运动伪影消失在脑电数据。 图8还显示一个次优的脑电图电极连接PO10发生在大约7秒。偶尔观察到这种行为是在实验过程中，可能是由于脑电图电极和头皮之间的接触的损失。电极PO10必须从这项试验的数据分析。由于脑电图的数据可以实时观察，验证脑电图电极连接在每项试验前在协议（协议第6.2步），穷人的电极连接可以补救之前试了下。 <table border="1"><tbody><tr><td> 名 </td><td> 公司 </td><td> 数量 </td></tr><tr><td> BrainAmp放大器lifier </td><td>脑产品，GMBH </td><td> 2 </td></tr><tr><td> actiCAP 64个电极脑电帽</td><td>脑产品，GMBH </td><td> 1 </td></tr><tr><td> Brainvision移动无线EEG系统</td><td>脑产品，GMBH </td><td> 1 </td></tr><tr><td>数据记录MWX8肌电图的数据采集单元</td><td>生物识别技术有限公司</td><td> 1 </td></tr><tr><td> SX230肌电电极</td><td>生物识别技术有限公司</td><td> 8 </td></tr><tr><td> R506 EMG接地电极</td><td>生物识别技术有限公司</td><td> 1 </td></tr><tr><td>蛋白石运行监测（玛格传感器） </td><td> APDM，INC。 </td><td> 11 </td></tr><tr><td>蛋白石基座无线数据流</td><td> APDM，INC。 </td><td> 2 </td></tr><tr><td>蛋白石无线接入点</td><td> APDM，INC。 </td><td> 2 </td></tr><tr><tD&gt;红外光栅套装MK120 </td><td> VELLEMAN，INC。 </td><td> 5 </td></tr><tr><td> Wixel可编程USB无线模块</td><td> pololu公司</td><td> 6 </td></tr></tbody></table> 表1中。设备。 <table border="1"><tbody><tr><td>传感器</td><td>位置</td></tr><tr><td>头</td><td>额头之上眉毛中心</td></tr><tr><td>树干</td><td>在胸鳍基部胸骨之间</td></tr><tr><td>腰</td><td>腰部曲线的最低回中心</td></tr><tr><td>臂1 </td><td>横向侧臂;由近端到手腕〜10％之间，以肘</td></tr><tr><td>大腿围1 </td><td>大腿外侧50％，髋关节和膝关节</td></tr><tr><td>柄1 </td><td>侧柄75％远端从膝盖</td></tr><tr><td>脚1 </td><td>围绕<html>脚背脚</td></tr><tr><td colspan="2"> 1手臂，大腿，小腿，足部传感器放置双边。 </td></tr></tbody></table> 表2。MARG传感器的位置。 <img alt="图1" fo:content-width="6.5in" fo:src="/files/ftp_upload/50602/50602fig1highres.jpg" src="/files/ftp_upload/50602/50602fig1.jpg" /> 图1矢状面（A）和额叶（二）鉴于主题穿着脑电图，肌电图，MARG惯性传感器采集数据。（三）在头皮上的脑电图电极位置的地形表示，绘制（与:Matlab工具箱EEGLAB 14。 D）含移动数据收集车主机电脑，手动触发，肌电蓝牙，玛格无线接入点，和脑电图的无线接收器，放大器和电源。d/50602/50602fig1large.jpg"目标="_blank"&gt;点击这里查看大图。 <img alt="图2" fo:content-width="6in" fo:src="/files/ftp_upload/50602/50602fig2highres.jpg" src="/files/ftp_upload/50602/50602fig2.jpg" /> 图2。详细定制设计的算法流程图，多线程的数据收集软件。 <a href="https://www.jove.com/files/ftp_upload/50602/50602fig2large.jpg" target="_blank">点击这里查看大图</a> 。 <img alt="图3" fo:content-width="4in" fo:src="/files/ftp_upload/50602/50602fig3highres.jpg" src="/files/ftp_upload/50602/50602fig3.jpg" /> 图3。舞台上行走（1）实验方案示意图（鸟瞰）表示。一个箭头（→，←，↑）呈现在显示屏上，当主体在入口处锥年底<html>秒。如果右（→）或左（←），主体如下红色或绿色的循环，分别通过四组的红外（IR）传感器（IR1-IR4）。如果选择了直线（↑），主体走向显示监视器（蓝线），和一个第二个箭头（→或←），提出在被摄物体前，IR传感器（IR5）约1米。通过通过IR5传感器集后，主体沿着其对应的路径（红色或绿色）完成循环，返回到起点。 <img alt="图4" fo:content-width="4in" fo:src="/files/ftp_upload/50602/50602fig4highres.jpg" src="/files/ftp_upload/50602/50602fig4.jpg" /> 图4。原理图（鸟瞰）表示的舞台上行走（2）的实验方案，在实验开始时，一个单一的箭头（pload/50602/50602larrhighres.jpg"/&gt; <img src="/files/ftp_upload/50602/50602rarr.jpg" alt="右箭头" fo:src="/files/ftp_upload/50602/50602rarrhighres.jpg" /> ，→，←，↑）呈现在显示监视器上的主体。主体走根据接收的箭头，直接的对应的一组红外传感器，通过传感器，在绕锥完成U形转弯，并返回到开始点（对应于循环<img src="/files/ftp_upload/50602/50602rarr.jpg" alt="右箭头" fo:src="/files/ftp_upload/50602/50602rarrhighres.jpg" />箭头所示）。 <img alt="图5" fo:content-width="5.5in" fo:src="/files/ftp_upload/50602/50602fig5highres.jpg" src="/files/ftp_upload/50602/50602fig5.jpg" /> 图5。从10秒的跑步机上行走。面板的样本数据显示64路频道名10-20国际公约的原始脑电数据。中间<html>面板显示11 MARG传感器在垂直方向上的加速度。底部面板显示8个通道原料肌电图<a href="https://www.jove.com/files/ftp_upload/50602/50602fig5large.jpg" target="_blank">点击这里查看大图</a> 。 <img alt="图6" fo:content-width="5.5in" fo:src="/files/ftp_upload/50602/50602fig6highres.jpg" src="/files/ftp_upload/50602/50602fig6.jpg" /> 图6。样本数据从一个循环（右箭头路径，图3）走在竞技场I协议。脑电图，加速度和肌电图的数据，如图5所示。垂直黑条由软件触发器的位置。第一触发器是从手动按钮启动循环凭→方向。以下四个触发器是来自红外传感器的红外图谱（IR1）-IR4为主题的遍历循环（ 图3）。tp_upload/50602/50602fig6large.jpg"目标="_blank"&gt;点击这里查看大图。 <img alt="图7" fo:content-width="5.5in" fo:src="/files/ftp_upload/50602/50602fig7highres.jpg" src="/files/ftp_upload/50602/50602fig7.jpg" /> 图7。样本数据从独立坐下来，坐 ​​，站过渡。脑电图，加速度，和肌电图的数据， 如图5所示。竖线表示手动触发（和音频线索）发起的站姿和坐姿，分别<a href="https://www.jove.com/files/ftp_upload/50602/50602fig7large.jpg" target="_blank">点击这里</a> 。 <a href="https://www.jove.com/files/ftp_upload/50602/50602fig7large.jpg" target="_blank">查看大图</a> 。 <img alt="图8" fo:content-width="5.5in" fo:src="/files/ftp_upload/50602/50602fig8highres.jpg" src="/files/ftp_upload/50602/50602fig8.jpg" /> 图8。从走廊行走的样品数据显示从斯坦过渡鼎行走和站立行走。脑电图，加速度，和肌电图的数据显示， 如图5所示。竖线表示手动触发和音频线索开始ANSD停止行走， <a href="https://www.jove.com/files/ftp_upload/50602/50602fig8large.jpg" target="_blank">点击这里查看大图</a> 。

Watch this Scientific Journal Video about Simultaneous Scalp Electroencephalography EEG, Electromyography EMG, and Whole-body Segmental Inertial Recording for Multi-modal Neural Decoding at JoVE.com

Simultaneous Scalp Electroencephalography EEG, Electromyography EMG, and Whole-body Segmental Inertial Recording for Multi-modal Neural Decoding

一个有效的脑机接口（BMI）系统的恢复和重建的两足动物运动的发展需要用户的意图准确的解码。在这里，我们提出了一种新的实验方案和数据收集技术，同时非侵入性收购的神经活动，肌肉活动，全身运动，在各种运动任务和条件。

同时头皮脑电图（EEG），肌电图（EMG）和全身分部惯性录制多模态神经解码

Recent  studies support the involvement of supraspinal networks in control of bipedal  human walking. Part of this evidence  encompasses studies, ...

simultaneous-scalp-electroencephalography-eeg-electromyography-emg

Research

JoVE Journal

Behavior

Simultaneous Scalp Electroencephalography (EEG), Electromyography (EMG), and Whole-body Segmental Inertial Recording for Multi-modal Neural Decoding

43.1K 次观看.  National Institutes of Health. 一个有效的脑机接口（BMI）系统的恢复和重建的两足动物运动的发展需要用户的意图准确的解码。在这里，我们提出了一种新的实验方案和数据收集技术，同时非侵入性收购的神经活动，肌肉活动，全身运动，在各种运动任务和条件。

视频: Simultaneous Scalp Electroencephalography EEG, Electromyography EMG, and Whole-body Segmental Inertial Recording for Multi-modal Neural Decoding

Method for Simultaneous fMRI/EEG Data Collection during a Focused Attention Suggestion for Differential Thermal Sensation

In the present work, we demonstrate a method for concurrent collection of EEG/fMRI data. In our setup, EEG data are collected using a high-density 256-channel sensor net. The EEG amplifier itself is contained in a field isolation containment system (FICS), and MRI clock signals are synchronized with EEG data collection for subsequent MR artifact characterization and removal. We demonstrate this method first for resting state data collection. Thereafter, we demonstrate a protocol for EEG/fMRI data recording, while subjects listen to a tape asking them to visualize that their left hand is immersed in a cold-water bath and referred to, here, as the cold glove paradigm. Thermal differentials between each hand are measured throughout EEG/fMRI data collection using an MR compatible temperature sensor that we developed for this purpose. We collect cold glove EEG/fMRI data along with simultaneous differential hand temperature measurements both before and after hypnotic induction. Between pre and post sessions, single modality EEG data are collected during the hypnotic induction and depth assessment process. Our representative results demonstrate that significant changes in the EEG power spectrum can be measured during hypnotic induction, and that hand temperature changes during the cold glove paradigm can be detected rapidly using our MR compatible differential thermometry device.

We present a protocol for concurrent collection of EEG/fMRI data, and synchronized MR clock signal recording. We demonstrate this method using a unique paradigm whereby subjects receive &#x2018;cold glove&#x2019; instructions during scanning, and EEG/fMRI data are recorded along with hand temperature measurements both before and after hypnotic induction.

微分热感集中注意建议期间同步 fMRI/EEG 数据收集方法

In the present work, we demonstrate a method for concurrent collection of EEG/fMRI data. In our setup, EEG data are collected using a high-density ...

科研

行为学

Best Current Practice for Obtaining High Quality EEG Data During Simultaneous fMRI

Simultaneous EEG-fMRI allows the excellent temporal resolution of EEG to be combined with the high spatial accuracy of fMRI. The data from these two modalities can be combined in a number of ways, but all rely on the acquisition of high quality EEG and fMRI data. EEG data acquired during simultaneous fMRI are affected by several artifacts, including the gradient artefact (due to the changing magnetic field gradients required for fMRI), the pulse artefact (linked to the cardiac cycle) and movement artifacts (resulting from movements in the strong magnetic field of the scanner, and muscle activity). Post-processing methods for successfully correcting the gradient and pulse artifacts require a number of criteria to be satisfied during data acquisition. Minimizing head motion during EEG-fMRI is also imperative for limiting the generation of artifacts.
Interactions between the radio frequency (RF) pulses required for MRI and the EEG hardware may occur and can cause heating. This is only a significant risk if safety guidelines are not satisfied. Hardware design and set-up, as well as careful selection of which MR sequences are run with the EEG hardware present must therefore be considered.
The above issues highlight the importance of the choice of the experimental protocol employed when performing a simultaneous EEG-fMRI experiment. Based on previous research we describe an optimal experimental set-up. This provides high quality EEG data during simultaneous fMRI when using commercial EEG and fMRI systems, with safety risks to the subject minimized. We demonstrate this set-up in an EEG-fMRI experiment using a simple visual stimulus. However, much more complex stimuli can be used. Here we show the EEG-fMRI set-up using a Brain Products GmbH (Gilching, Germany) MRplus, 32 channel EEG system in conjunction with a Philips Achieva (Best, Netherlands) 3T MR scanner, although many of the techniques are transferable to other systems.

Simultaneous electroencephalography (EEG) and functional Magnetic Resonance imaging (fMRI) is a powerful neuroimaging tool. However, the inside of an MRI scanner forms a difficult environment for EEG data recording and safety must be considered whenever operating EEG equipment inside a scanner. Here, we present an optimised EEG-fMRI data acquisition protocol.

获得高质量的脑电数据在同步功能磁共振成像的当前最佳实践

Simultaneous  EEG-fMRI allows the excellent temporal resolution of EEG to be combined with the  high spatial accuracy of fMRI. The data  from these two ...

Simultaneous EEG Monitoring During Transcranial Direct Current Stimulation

Transcranial direct current stimulation (tDCS) is a technique that delivers weak electric currents through the scalp. This constant electric current induces shifts in neuronal membrane excitability, resulting in secondary changes in cortical activity. Although tDCS has most of its neuromodulatory effects on the underlying cortex, tDCS effects can also be observed in distant neural networks. Therefore, concomitant EEG monitoring of the effects of tDCS can provide valuable information on the mechanisms of tDCS. In addition, EEG findings can be an important surrogate marker for the effects of tDCS and thus can be used to optimize its parameters. This combined EEG-tDCS system can also be used for preventive treatment of neurological conditions characterized by abnormal peaks of cortical excitability, such as seizures. Such a system would be the basis of a non-invasive closed-loop device. In this article, we present a novel device that is capable of utilizing tDCS and EEG simultaneously. For that, we describe in a step-by-step fashion the main procedures of the application of this device using schematic figures, tables and video demonstrations. Additionally, we provide a literature review on clinical uses of tDCS and its cortical effects measured by EEG techniques.

Transcranial direct current stimulation (tDCS) is a non-invasive brain stimulation technique that has shown initial therapeutic effects in several neurological conditions. The main mechanism underlying these therapeutic effects is the modulation of cortical excitability. Therefore, online monitoring of cortical excitability would help guide stimulation parameters and optimize its therapeutic effects. In the present article we review the use of a novel device that combines simultaneous tDCS and EEG monitoring in real time.

同时脑电图监测在经颅直流电刺激

Transcranial  direct current stimulation (tDCS) is a technique that delivers weak electric  currents through the scalp. This constant electric current ...

Functional Near Infrared Spectroscopy of the Sensory and Motor Brain Regions with Simultaneous Kinematic and EMG Monitoring During Motor Tasks

There are several advantages that functional near-infrared spectroscopy (fNIRS) presents in the study of the neural control of human movement. It is relatively flexible with respect to participant positioning and allows for some head movements during tasks. Additionally, it is inexpensive, light weight, and portable, with very few contraindications to its use. This presents a unique opportunity to study functional brain activity during motor tasks in individuals who are typically developing, as well as those with movement disorders, such as cerebral palsy. An additional consideration when studying movement disorders, however, is the quality of actual movements performed and the potential for additional, unintended movements. Therefore, concurrent monitoring of both blood flow changes in the brain and actual movements of the body during testing is required for appropriate interpretation of fNIRS results. Here, we show a protocol for the combination of fNIRS with muscle and kinematic monitoring during motor tasks. We explore gait, a unilateral multi-joint movement (cycling), and two unilateral single-joint movements (isolated ankle dorsiflexion, and isolated hand squeezing). The techniques presented can be useful in studying both typical and atypical motor control, and can be modified to investigate a broad range of tasks and scientific questions.

Monitoring brain activity during upright motor tasks is of great value when investigating the neural source of movement disorders. Here, we demonstrate a protocol that combines functional near infrared spectroscopy with continuous monitoring of muscle and kinematic activity during 4 types of motor tasks.

感觉和运动脑区与运动同步和肌电图监测功能近红外光谱在运动任务

There are several advantages that functional near-infrared spectroscopy (fNIRS) presents in the study of the neural control of human movement. It is ...

Utilizing Electroencephalography Measurements for Comparison of Task-Specific Neural Efficiencies: Spatial Intelligence Tasks

Spatial intelligence is often linked to success in engineering education and engineering professions. The use of electroencephalography enables comparative calculation of individuals&#39; neural efficiency as they perform successive tasks requiring spatial ability to derive solutions. Neural efficiency here is defined as having less beta activation, and therefore expending fewer neural resources, to perform a task in comparison to other groups or other tasks. For inter-task comparisons of tasks with similar durations, these measurements may enable a comparison of task type difficulty. For intra-participant and inter-participant comparisons, these measurements provide potential insight into the participant&#39;s level of spatial ability and different engineering problem solving tasks. Performance on the selected tasks can be analyzed and correlated with beta activities. This work presents a detailed research protocol studying the neural efficiency of students engaged in the solving of typical spatial ability and Statics problems. Students completed problems specific to the Mental Cutting Test (MCT), Purdue Spatial Visualization test of Rotations (PSVT:R), and Statics. While engaged in solving these problems, participants&#39; brain waves were measured with EEG allowing data to be collected regarding alpha and beta brain wave activation and use. The work looks to correlate functional performance on pure spatial tasks with spatially intensive engineering tasks to identify the pathways to successful performance in engineering and the resulting improvements in engineering education that may follow.

This manuscript describes an approach to measure neural activity of humans while solving spatially focused engineering problems. The electroencephalogram methodology helps interpret beta brain wave measurements in terms of neural efficiency, with the aim of ultimately enabling comparisons of task performance both between problem types and between participants.

利用脑电图测量任务特定神经效率的比较:空间智能任务

Spatial intelligence is often linked to success in engineering education and engineering professions. The use of electroencephalography enables ...

A Novel Experimental and Analytical Approach to the Multimodal Neural Decoding of Intent During Social Interaction in Freely-behaving Human Infants

Understanding typical and atypical development remains one of the fundamental questions in developmental human neuroscience. Traditionally, experimental paradigms and analysis tools have been limited to constrained laboratory tasks and contexts due to technical limitations imposed by the available set of measuring and analysis techniques and the age of the subjects. These limitations severely limit the study of developmental neural dynamics and associated neural networks engaged in cognition, perception and action in infants performing &#8220;in action and in context&#8221;. This protocol presents a novel approach to study infants and young children as they freely organize their own behavior, and its consequences in a complex, partly unpredictable and highly dynamic environment. The proposed methodology integrates synchronized high-density active scalp electroencephalography (EEG), inertial measurement units (IMUs), video recording and behavioral analysis to capture brain activity and movement non-invasively in freely-behaving infants. This setup allows for the study of neural network dynamics in the developing brain, in action and context, as these networks are recruited during goal-oriented, exploration and social interaction tasks.

This protocol presents a novel methodology for the neural decoding of intent from freely-behaving infants during unscripted social interaction with an actor. Neural activity is acquired using non-invasive high-density active scalp electroencephalography (EEG). Kinematic data is collected with inertial measurement units and supplemented with synchronized video recording.

在自由，表现人类婴儿一种新的实验和分析方法意向的多模态神经解码期间社会互动

Understanding typical and atypical development remains one of the fundamental questions in developmental human neuroscience. Traditionally, experimental ...

Concurrent Electroencephalography Recording During Transcranial Alternating Current Stimulation (tACS)

Oscillatory brain activities are considered to reflect the basis of rhythmic changes in transmission efficacy across brain networks and are assumed to integrate cognitive neural processes. Transcranial alternating current stimulation (tACS) holds the promise to elucidate the causal link between specific frequencies of oscillatory brain activity and cognitive processes. Simultaneous electroencephalography (EEG) recording during tACS would offer an opportunity to directly explore immediate neurophysiological effects of tACS. However, it is not trivial to measure EEG signals during tACS, as tACS creates a huge artifact in EEG data. Here we explain how to set up concurrent tACS-EEG experiments. Two necessary considerations for successful EEG recording while applying tACS are highlighted. First, bridging of the tACS and EEG electrodes via leaking EEG gel immediately saturates the EEG amplifier. To avoid bridging via gel, the viscosity of the EEG gel is the most important parameter. The EEG gel must be viscous to avoid bridging, but at the same time sufficiently fluid to create contact between the tACS electrode and the scalp. Second, due to the large amplitude of the tACS artifact, it is important to consider using an EEG system with a high resolution analog-to-digital (A/D) converter. In particular, the magnitude of the tACS artifact can exceed 100 mV at the vicinity of a stimulation electrode when 1 mA tACS is applied. The resolution of the A/D converter is of importance to measure good quality EEG data from the vicinity of the stimulation site. By following these guidelines for the procedures and technical considerations, successful concurrent EEG recording during tACS will be realized.

Concurrent Electroencephalography Recording During Transcranial Alternating Current Stimulation tACS

In this article we explain how to set up a concurrent transcranial alternating current stimulation and EEG experiment.

并行脑电图记录在经颅交流电刺激（TACS）

Oscillatory brain activities are considered to reflect the basis of rhythmic changes in transmission efficacy across brain networks and are assumed to ...

Determining Pain Detection and Tolerance Thresholds Using an Integrated, Multi-Modal Pain Task Battery

Human pain models are useful in the assessing the analgesic effect of drugs, providing information about a drug&#39;s pharmacology and identify potentially suitable therapeutic populations. The need to use a comprehensive battery of pain models is highlighted by studies whereby only a single pain model, thought to relate to the clinical situation, demonstrates lack of efficacy. No single experimental model can mimic the complex nature of clinical pain. The integrated, multi-modal pain task&#160;battery presented here encompasses the electrical stimulation task, pressure stimulation task, cold pressor task, the UVB inflammatory model which includes a thermal task and a paradigm for inhibitory conditioned pain modulation. These human pain models have been tested for predicative validity and reliability both in their own right and in combination, and can be used repeatedly, quickly, in short succession, with minimum burden for the subject and with a modest quantity of equipment. This allows a drug to be fully characterized and profiled for analgesic effect which is especially useful for drugs with a novel or untested mechanism of action.

Human pain models are valuable tools used to assess the analgesic potential of novel compounds and predict their clinical efficacy, especially when used in an integrated manner. Although implementation of these models is complex, with proper execution, the pain models described in this protocol can provide predictive and reliable results.

确定疼痛的检测和容忍阈值使用集成的，多模式疼痛任务电池

Human pain models are useful in the assessing the analgesic effect of drugs, providing information about a drug&#39;s pharmacology and identify ...

Using Laser Doppler Imaging and Monitoring to Analyze Spinal Cord Microcirculation in Rat

Laser Doppler flowmetry (LDF) is a noninvasive method for blood flow (BF) measurement, which makes it preferable for measuring microcirculatory alterations of the spinal cord. In this article, our goal was to use both Laser Doppler imaging and monitoring to analyze the change of BF after spinal cord injury. Both the laser Doppler image scanner and the probe/monitor were being employed to obtain each readout. The data of LDPI provided a local distribution of BF, which gave an overview of perfusion around the injury site and made it accessible for comparative analysis of BF among different locations. By intensely measuring the probing area over a period of time, a combined probe was used to simultaneously measure the BF and oxygen saturation of the spinal cord, showing overall spinal cord perfusion and oxygen supply. LDF itself has a few limitations, such as relative flux, sensitivity to movement, and biological zero signal. However, the technology has been applied in clinical and experimental study due to its simple setup and rapid measurement of BF.

Here we present a combination of laser Doppler perfusion imaging (LDPI) and laser Doppler perfusion monitoring (LDPM) to measure spinal cord local blood flows and oxygen saturation (SO2), as well as a standardized procedure for introducing spinal cord trauma on rat.

激光多普勒成像与监测在大鼠脊髓微循环分析中的应用

Laser Doppler flowmetry (LDF) is a noninvasive method for blood flow (BF) measurement, which makes it preferable for measuring microcirculatory ...

A Wireless, Bidirectional Interface for In Vivo Recording and Stimulation of Neural Activity in Freely Behaving Rats

In vivo electrophysiology is a powerful technique to investigate the relationship between brain activity and behavior at a millisecond and micrometer scale. However, current methods mostly rely on tethered cable recordings or only use unidirectional systems, allowing either recording or stimulation of neural activity, but not at the same time or same target. Here, a new wireless, bidirectional device for simultaneous multichannel recording and stimulation of neural activity in freely behaving rats is described. The system operates through a single portable head stage that both transmits recorded activity and can be targeted in real-time for brain stimulation using a telemetry-based multichannel software. The head stage is equipped with a preamplifier and a rechargeable battery, allowing stable long-term recordings or stimulation for up to 1 h. Importantly, the head stage is compact, weighs 12 g (including battery) and thus has minimal impact on the animal&#180;s behavioral repertoire, making the method applicable to a broad set of behavioral tasks. Moreover, the method has the major advantage that the effect of brain stimulation on neural activity and behavior can be measured simultaneously, providing a tool to assess the causal relationships between specific brain activation patterns and behavior. This feature makes the method particularly valuable for the field of deep brain stimulation, allowing precise assessment, monitoring, and adjustment of stimulation parameters during long-term behavioral experiments. The applicability of the system has been validated using the inferior colliculus as a model structure.