CN110665114B - 具有小尺寸发射天线的远程rf功率系统 - Google Patents
具有小尺寸发射天线的远程rf功率系统 Download PDFInfo
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Abstract
一种天线组件，包括：天线，所述天线包括：具有辐射表面的金属信号层，和馈入端口；以及波导，其包围天线并且被配置用于在远离天线的方向上引导从辐射表面发射的电磁能；和控制器模块，其被连接到所述馈入端口并且被配置用于驱动天线以从辐射表面发射电磁能；其中，所述天线、波导和控制器模块被构造成使得，当控制器模块驱动天线时，所发射的电磁能匹配可植入装置的接收特征并且，在所述可植入装置被设置为距天线至少10厘米时，足以使可植入装置仅仅利用从天线接收的电磁能即可制造振幅足以刺激患者的神经组织的一个或多个电脉冲。
Description
本申请是2015年5月12日提交的申请号为“201580036252.2”发明名称为“具有小尺寸发射天线的远程RF功率系统”的发明专利申请的分案申请。
相关申请的交叉引用
本申请要求于2014年5月12日提交的美国临时专利申请61/992,150的权益，该申请被整体以引用方式并入本文。
技术领域
本申请总体上涉及包括向可植入装置远程提供功率和刺激参数的天线组件的RF刺激系统。
背景技术
天线已经被设计出来并且与被植入装置一起使用，来帮助多种医学条件下的治疗。通常，这些天线被靠近患者身体放置。在一些情况下，天线的导电元件过度地吸收电磁能，当这些天线靠近患者身体放置时，这会引起不利的事件，比如组织燃烧、不期望的血块以及由于天线直接粘附到皮肤组织而引起的皮肤刺激。
发明内容
在一个方面中，一些实施方式提供了一种天线组件，包括：天线，所述天线包括：具有辐射表面的金属信号层，和馈入端口；以及波导，其包围天线并且被配置用于在远离天线的方向上引导从辐射表面发射的电磁能；和控制器模块，其被连接到所述馈入端口并且被配置用于驱动天线以从辐射表面发射电磁能；其中，所述天线、波导和控制器模块被构造成使得，当控制器模块驱动天线时，所发射的电磁能匹配可植入装置的接收特征并且，在所述可植入装置被设置为距天线至少10厘米时，足以使可植入装置仅仅利用从天线接收的电磁能即可制造振幅足以刺激患者的神经组织的一个或多个电脉冲。
实施方式可包括下述特征中的一个或多个。天线组件可还包括介质透镜，其充填波导并且从波导的开口向外突伸以形成突出部，所述突出部被成形为使所发射的电磁能在远离发射表面的方向上在空间上缩窄。所述突出部可被制成锥形渐缩形状。所述突出部可被制成锥形渐缩而具有高斯或正弦曲线轮廓。
所述天线组件可具有与波导相关联的回波损耗截止频率并且所述介质透镜可被进一步配置用于降低回波损耗截止频率。所述天线可在从约500MHz至约4GHz的频带内可操作。所述辐射表面可以是蝶形的并且具有两个叶结构，所述两个叶结构在馈入端口处通过两个大致平行的杆结构连接到彼此。所发射的电磁能可被沿着杆结构的长轴极化。所述辐射表面可以是从第一空间定向至第二空间定向可调节的以使在可植入装置处接收的极化电磁能增加。
所述波导可以是矩形波导，所述矩形波导具有包围所述蝶形的辐射表面的四个壁。所述矩形波导可具有约15cm的内部长度，约7.6cm的内部宽度，和约5cm的高度。所述矩形波导可具有至少10cm的内部长度，所述矩形波导可具有约为15:7.6:5的内部长度、宽度、和高度比。
在另一个方面中，一些实施方式可包括一种向可植入装置无线供应能量的方法，所述方法包括：从天线组件上的辐射表面辐射电磁能，被辐射的电磁能到达可植入装置，所述可植入装置被设置在至少10厘米远处并且被植入患者体内，使得可植入装置仅仅通过利用所辐射的电磁能即可制造适合于刺激患者的神经组织的一个或多个电刺激脉冲并且将所述电刺激脉冲应用到患者的神经组织。
实施方式可包括下述特征中的一个或多个。辐射电磁能还包括在患者睡着时辐射电磁能，使得被制造的所述一个或多个电刺激脉冲在患者睡着期间被应用而刺激患者的神经组织。
所述方法可还包括：调节天线组件的位置使得天线组件的辐射表面距离可植入装置不大于六英尺。所述方法可还包括：调节天线组件的位置使得天线组件的辐射表面距离可植入装置不小于一英尺。所述方法可还包括：调节天线组件的定向使得在可植入装置处接收的被辐射电磁能增加。所述方法可还包括：将天线组件连接到控制器模块；和从连接于其上的控制器模块驱动天线组件，使天线组件上的辐射表面辐射电磁能以启动可植入装置。所述方法可还包括：建立编程模块至控制器模块之间的链接；和从编程模块向控制器模块发射对将在可植入装置处制造以及随后被应用于刺激患者的神经组织的所述一个或多个刺激脉冲的参数编码的数据。
在又另一方面中，一些实施方式可包括一种系统，该系统包括：无线启动可植入装置的天线组件，天线组件包括：天线，所述天线包括：金属信号层，其具有辐射表面并且被配置为经由辐射耦合而发射电磁能；波导，其包围天线并且被配置用于在远离天线的方向上引导从辐射表面发射的电磁能；和；控制器模块，其被连接到天线的馈入端口并且被配置用于驱动天线组件以使天线上的辐射表面辐射电磁能。
实施方式可包括下述特征中的一个或多个。所述系统可还包括可植入装置，其从患者体内的一位置可操作并且距离天线组件大于10厘米，其中，可植入装置仅仅利用从天线组件接收的电磁能即制造振幅足以刺激患者的神经组织的一个或多个刺激脉冲。
所述波导可以是具有包围辐射表面的四个壁的矩形波导。所述矩形波导可具有约15cm的内部长度，约7.6cm的内部宽度，和约5cm的高度。所述矩形波导可具有至少10cm的内部长度，并且所述矩形波导可具有约为15:7.6:5的内部长度、宽度、和高度比。
所述系统可还包括介质透镜，其充填波导并且从波导的开口向外突伸以形成突出部，所述突出部被成形为使所发射的电磁能在远离发射表面的方向上在空间上缩窄。所述突出部可被制成锥形渐缩形状。所述突出部可被制成锥形渐缩而具有高斯或正弦曲线轮廓。
所述天线可以是在从约500MHz至约4GHz的频带内可操作的。所述辐射表面可以是蝶形的并且具有两个叶结构，所述两个叶结构在馈入端口处通过两个大致平行的杆结构连接到彼此。
所发射的电磁能可被沿着杆结构的长轴极化。所述可植入装置可包括设置在患者体内的可植入装置上的偶极天线，并且所述辐射表面是从第一空间定向至第二空间定向可调节的以使在偶极天线处接收的极化电磁能增加。
附图说明
图1描绘出无线刺激系统的例子的高级概要图。
图2描绘出无线刺激系统的例子的细节图。
图3A-3C示出微波刺激系统的操作的例子。
图4A-4B示出当微波刺激系统处于操作中时的辐射空间区域的例子。
图5A-5B示出了无线刺激系统的天线组件的例子。
图6A-6C是带波导的天线组件的示意图。
图7示出了图6A-6C的天线组件的回波损耗特征的例子。
图8示出了在约915MHz处共振的天线组件的模拟回波损耗特征的例子。
图9A-9B示出了来自图8的天线组件的模拟电磁辐射图的例子。
图10示出了包括蝶形辐射表面、波导、和介质透镜的天线组件的例子。
图11A-11B示出了图10的天线组件的模拟回波损耗和发射特征。
图12示出了来自图10的天线组件的模拟电磁辐射图的立体图。
图13A-13B示出了图12的模拟电磁辐射图的X-Z和Y-Z平面图。
不同图中类似的参考标记表示类似的部件。
具体实施方式
在各实施方式中，公开了向目标可刺激组织、比如神经应用一个或多个电脉冲的系统和方法，用于治疗慢性疼痛，炎症，关节炎，睡眠呼吸暂停，病情突发，大小便失禁，与癌症相关的疼痛，大小便失禁，运动开始与控制的问题，不自主运动，血管功能不全，心率不齐，肥胖症，糖尿病，颅面痛、比如偏头痛或丛集性头痛，以及其它身心机能失调。在某些实施例中，一装置可被用于，通过在不使用缆线或感应耦合的情况下利用远程射频(RF)能量，发送电能至目标神经组织，以启动无源的被植入无线刺激器装置。这些目标神经可包括、但不限于脊髓和周围区域，包括背角，背根节，存在的神经根，神经节，背柱纤维和离开背柱和脑的周围神经束，比如迷走神经，枕骨，三叉神经，舌下神经，骶椎，尾神经等。
无线刺激系统可包括带有一个或多个电极和一个或多个导电天线(例如，偶极或贴片天线)的可植入刺激器装置，以及用于频率波形和电能整流的内部电路。该系统可还包括外部控制器和天线，用于在既不用缆线也不用感应耦合的方式从外部源向可植入刺激器装置发射射频或微波能量以提功率。
在各种实施方式中，无线的可植入刺激器装置被以无线方式启动(并且因此不需要有线连接)，并且包含从体外源接收脉冲指令所必须的电路。例如，各实施例采用内部偶极(或其它)天线配置来通过电辐射耦合接收RF功率。这允许这种装置在不用物理连接到可植入脉冲反生器(IPG)的情况下或不使用感应线圈的情况下产生能够刺激神经束的电流。
天线可被设计用于从一遥远位置(例如，多达四至六英尺并且静止不动)向接收天线发射微波能量的目的，所述接收天线位于患者的皮肤下面，或位于皮肤上。该天线设计可取决于患者在接受治疗的同时进行移动的需求。天线具有小尺寸可能是有利的，这样天线就可以与房间的周围环境协调。本公开聚焦于具有较好的匹配和收益的、紧凑的远程发射天线设计，比同类天线便宜若干数量级以及更容易制造。
根据一些实施方式，无线刺激系统可包括天线组件，其被耦合至控制器模块并且被配置用于向可植入装置辐射电磁能。在一些例子中，可植入装置可以是被配置用于以无线方式接收RF能量和刺激参数的无源神经刺激器装置。仅仅通过使用所接收的电磁能，可植入的无源神经刺激器制造一个或多个刺激脉冲来刺激患者的神经组织。特别地，天线组件可包括具有蝶形辐射表面和馈入端口的天线。馈入端口可被耦合到控制器模块，所述控制器模块驱动天线以从蝶形辐射表面发射电磁能。蝶形辐射表面被总体上设计尺寸和形状为辐射电磁能，以匹配可植入的无源神经刺激器的接收特征。在一个例子中，可植入的无源神经刺激器包括偶极天线，并且所述辐射表面被配置用于发射与偶极接收特征相应的极化(polarized)电磁能。而且，天线组件可还包括波导，其包围天线以远离所述辐射表面引导所发射的电磁能。在一些例子中，介质透镜充满(fill)波导并且从波导的开口向外延伸以形成突出部。该突出部被成形为使所发射的电磁能在远离发射表面的方向上在空间上缩窄。该突出部在形状上可被制成锥形并且可具有高斯或正弦曲线轮廓。
用于向患者提供神经刺激的示例性无线系统的进一步介绍可在下述共同拥有的、已公布的待审PCT申请中找到：2011年1月28日提交的PCT/US2012/23029，2011年4月11日提交的PCT/US2012/32200，2011年1月28日提交的PCT/US2012/48903，2011年8月12日提交的PCT/US2012/50633和2011年9月15日提交的PCT/US2012/55746，这些申请被以引用方式并入本文。
图1描绘了无线刺激系统的例子的高级概要图。无线刺激系统可包括四个主要部件，即，程序设计器模块102，RF脉冲发生器模块106，发射(TX)天线110(例如，贴片天线、槽缝天线、或偶极天线)，和被植入无线刺激器装置114。程序设计器模块102可以是运行支持无线连接104的软件应用、比如
的计算机装置，比如智能手机。本申请可使使用者能够观察系统状态和诊断情况，改变各参数，增大/减小电极脉冲的预期刺激振幅，和调节RF脉冲发生器模块106的反馈敏感性，以及其它功能。
RF脉冲发生器模块106可包括支持无线连接104的通信电子器件，刺激电路，和为发生器电子器件供电的电池。在一些实施方式中，RF脉冲发生器模块106包括嵌到其包装尺寸外型(form factor)内的TX天线，而在其它实施方式中，TX天线被通过有线连接108或无线连接(未示出)连接到RF脉冲发生器模块106。TX天线110可被直接耦合到组织，以制造启动被植入无线刺激器装置114的电场。TX天线110通过RF接口与被植入无线刺激器装置114通信。例如，TX天线110辐射RF发射信号，该信号通过RF脉冲发生器模块110调制和编码。模块114的被植入无线刺激器装置包含一个或多个天线，比如偶极天线，用于通过RF接口112接收和传输。特别地，天线110与模块114的被植入无线刺激装置上的所述一个或多个天线之间的耦合机构利用的是电辐射耦合并且不是感应耦合。换句话说，此耦合是通过电场，而不是磁场。
通过此电辐射耦合，TX天线110可向被植入无线刺激器装置114提供输入信号。此输入信号包含能量并且可包含对将在被植入无线刺激器装置114的电极处应用的刺激波形进行编码的信息。在一些实施方式中，此输入信号的功率水平直接决定利用包含在该输入信号中的电能产生的所述一个或多个电脉冲的应用振幅(例如，功率，电流，或电压)。在被植入无线刺激器装置114内具有用于解调RF发射信号的部件，和用于向周围的神经组织传递刺激的电极。
RF脉冲发生器模块106可被皮下植入，或它可被穿戴在体外。当在体外时，RF发生器模块106可被合并到带或背带设计中，以允许穿过皮肤和下面的组织的电辐射耦合，向被植入无线刺激器装置114传递功率和/或控制参数。在任一情况下，无线刺激器装置114内部的接收器电路可捕捉由TX天线110辐射的能量并且将此能量转换成电波形。接收器电路可进一步修改该波形以制造适合于神经组织的刺激的电脉冲。
在一些实施方式中，RF脉冲发生器模块106可远程控制刺激参数(即，应用于神经组织的电脉冲的参数)和基于从被植入无线刺激器装置114接收的RF信号监控来自无线刺激器装置114的反馈。通过RF脉冲发生器模块106实施的反馈检测算法可监控从被植入无线刺激器装置114无线发送的数据，该数据包括与被植入无线刺激器装置114正在从RF脉冲发生器接收的能量有关的信息以及与正在被传递至电极垫的刺激波形有关的信息。为了在给定医疗条件下提供有效治疗，该系统可被调节，以通过电刺激向神经纤维提供最佳量值的应激或抑制。闭环反馈控制方法可被使用，其中来自被植入无线刺激器装置114的输出信号被监控并且被用于确定适当水平的神经刺激电流用于维持有效的神经活动，或者，在一些情况下，在开环控制方法中患者可手动调节输出信号。
图2绘示了无线刺激系统的例子的详细图示。如图所示，编程模块102可包括用户输入系统202和通信子系统208。用户输入系统221可允许各参数设置被用户以指令组的形式进行调节(在一些情况下，在开环形式中)。通信子系统208可经由无线连接104、比如Bluetooth或Wi-Fi向RF脉冲发生器模块106发射这些指令组(以及其它信息)，以及从模块106接收数据。
例如，程序设计器模块102可为多个用户使用，比如患者的控制单元或临床医生的程序设计器单元，可被用于发送刺激参数至RF脉冲发生器模块106。可被控制的刺激参数可包括如表1中所示范围内的脉冲振幅、脉冲频率、和脉冲宽度。本文中，术语脉冲是指直接产生该组织的刺激的波形相位；电荷平衡相位的参数(在下面描述的)可类似地进行控制。患者和/或临床医生也可以可选地控制治疗的总体持续时间和模式。
刺激参数表1
脉冲振幅：0至20mA
脉冲频率：0至10000Hz
脉冲宽度：0至2ms
在初始植入手术期间，RF脉冲发生器模块106可初始时被编程为满足用于每一单个患者的特殊参数设置。因为医疗条件或身体本身可能随时间变化，能够重新调节参数设置可能是有益的，以确保神经调节疗法的持续功效。
程序设计器模块102在功能上可以是智能装置和相关的应用装置。智能装置的硬件可包括CPU 206，并且可被用作媒介物用于处理在图形用户界面(GUI)204上的触摸屏输入，进行处理和存储数据。
RF脉冲发生器模块106可经由有线连接108连接到外部TX天线110。可选地，天线和RF脉冲发生器两者都被皮下设置(未示出)。
由RF脉冲发生器模块106发送至被植入无线刺激器装置114的信号可包括功率和参数设置属性两者，关于刺激波形、振幅、脉冲宽度、和频率。RF脉冲发生器模块106可还用作从被植入无线刺激器装置114接收反馈信号的无线接收单元。为此目的，RF脉冲发生器模块106可包含，用于处理被发射至装置114的信号的产生以及用于处理反馈信号、比如来自刺激器装置114的那些信号，的微电子器件或其它电路。例如，RF脉冲发生器模块106可包括控制器子系统214，高频振荡器218，RF放大器216，RF开关，和反馈子系统212。
控制器子系统214可包括用于处理数据处理的CPU 230，存储子系统228、比如本地存储器，与程序设计器模块102通信(包括从程序设计器模块接收刺激参数)的通信子系统234，脉冲发生器电路236，和数字/模拟(D/A)转换器232。
控制器子系统214可被患者和/或临床医生使用，用于控制刺激参数设置(例如，通过控制从RF脉冲发生器模块106发送至刺激器装置114的信号的参数)。例如，这些参数设置能够影响所述一个或多个电脉冲的功率、电流水平、或形状。对刺激参数的编程可使用编程模块102进行，如上所述，以设置通过RF能量发射至被植入无线刺激装置214中的接收(RX)天线238、典型地偶极天线(但其它类型可被使用)的重复率、脉冲宽度、振幅、和波形。临床医生可选择将某些设置锁定和/或隐藏在程序设计器接口内，从而限制患者观察或调节某些参数的能力，因为某些参数的调整可能需要神经心理学、神经解剖学、神经调控协议、和电刺激的安全极限的详细医学知识。
控制器子系统214可将所接收的参数设置存储在当地存储器子系统228中，直到这些参数设置被从编程模块102接收的新输入数据修改。CPU 206可使用存储在当地存储器装置中的参数来控制脉冲发生器电路236，以产生刺激波形，该波形通过从300MHz至8GHz范围内(优选约700MHz和5.8GHz之间并且更优选约800MHz和1.3GHz之间)的高频振荡器218调制。所生成的RF信号可被RF放大器226放大，然后通过RF开关223发送至TX天线110，穿过组织的深度到达RX天线238。
在一些实施方式中，通过TX天线110发射的RF信号简单地来说可以是被无线刺激装置模块114使用用来产生电脉冲的功率发射信号。在其它实施方式中，遥测信号也可被发射到无线刺激器装置114，以发送有关无线刺激器装置114的各操作的指令。遥测信号可通过载体信号的调制而发送(如果在外面则穿过皮肤，或如果脉冲发生器模块106被皮下植入则穿过其它身体组织)。遥测信号被用于调制该载体信号(高频信号)，所述载体信号被耦合到植入天线238但不与在同一刺激器装置上接收的输入干涉，用于启动该装置。在一个实施例中，遥测信号和启动信号被结合成一个信号，其中RF遥测信号被用于调制RF启动信号，因此无线刺激装置通过所接收的遥测信号直接启动；无线刺激装置中的分离的子系统利用包含在信号中的功率并且解释信号的数据内容。
RF开关223可以是多功能器件、比如双定向耦合器，其以最小的插入损耗将相对高振幅的、极短持续时间的RF脉冲传递至TX天线110，同时提供两个低水平输出至反馈子系统212；一个输出传递前向功率信号至反馈子系统212，其中前向功率信号是被发送至TX天线110的RF脉冲的衰减形式，另一输出传递反向功率信号至反馈子系统212的不同端口，其中反向功率是来自TX天线110的反射RF能的衰减形式。
在运转周期时间期间(其中RF信号被发射至无线刺激器装置114)，RF开关223被设定为向反馈子系统发送前向功率信号。在停止运转周期时间期间(其中RF信号不被发射至无线刺激器装置114)，RF开关223可变化至接收模式，其中来自无线刺激器装置114的反射RF能和/或RF信号被接收，以在反馈子系统212中进行分析。
RF脉冲发生器模块106的反馈子系统212可包括接收电路，用于接收和提取来自无线刺激器装置114的遥测或其它反馈信号，和/或来自TX天线110发射的信号的反射RF能。反馈子系统可包括放大器226，滤波器224，解调器222，和AID转换器220。
反馈子系统212接收前向功率信号并且将此高频AC信号转换成能够被取样和发送到控制器子系统214的DC水平。以这种方式，所生成的RF脉冲的特征可被与控制器子系统214内的参考信号进行比较。如果在任一参数中存在差异(误差)，则控制器子系统214可以调控至RF脉冲发生器106的输出。例如，该调节的特性可与计算误差成比例。控制器子系统214可在其调控方案上引入另外的输入并且限制，比如反向功率的信号振幅和各脉冲参数的任何预定最大或最小值。
反向功率信号可被用于检测RF功率传递系统中的故障环境。在理想环境下，当TX天线110具有与其接触的组织完美匹配的阻抗时，从RF脉冲发生器106产生的电磁波将不受阻地从TX天线110传递到身体组织内。然而，在现实应用中，在用户的身体体型、所穿戴的衣服类型、以及天线110相对于身体表面的定位方面可能存在较大程度的变化性。因为天线110的阻抗取决于下面的组织和任何介入材料的相对介电常数，并且还取决于天线距皮肤的总体间隔距离，在任何给定应用中，在TX天线110与身体表面的接口处都可能阻抗的不匹配。当发生这种不匹配时，从RF脉冲发生器106发出的电磁波就会在此接口处部分地反射，并且此反射的能量向回传播通过天线馈送装置。
双定向耦合器RF开关223可防止被反射的RF能向回传播到放大器226内，并且可减弱此反射RF信号以及将被减弱的信号作为反向功率信号发射至反馈子系统212。反馈子系统212可将此高频AC信号转换成能够进行取样并且发送到控制器子系统214的DC水平。然后，控制器子系统214可以计算反向功率信号的振幅与前向功率信号的振幅的比。反向功率信号的振幅与前向功率信号的振幅的比可以表示阻抗不匹配的严重性。
为了感测阻抗匹配环境，控制器子系统214可实时测量反射功率比，并且根据此测量的预设临界值，控制器子系统214可修改由RF脉冲发生器106产生的RF功率的水平。例如，对于中等程度的反射功率来说，采取的方案可以是控制器子系统214增大被发射到TX天线110的RF功率的振幅，如用于补偿TX天线至身体的耦合轻微不佳、但可接受的情况时所需要的那样。对于较高比值的反射功率来说，采取的方案可以是禁止RF脉冲发生器106操作并且设定表示TX天线110与身体很少地耦合或没有耦合的错误代码。这种类型的反射功率故障环境也可能由至TX天线的不良连接或断开的连接产生。在任一情况下，当反射功率比高于预定临界值时都可能希望停止RF发射，因为内部反射的功率可导致不希望的加热内部部件，并且此故障环境意味着本系统不能传递足够的功率至被植入无线刺激装置因而不能向用户传递疗法。
在接收循环期间，无线刺激器装置114的控制器242可通过天线238发射报告信号、比如遥测信号，以与RF脉冲发生器模块106通信。例如，在晶体管电路的通和断状态期间，来自无线刺激器装置114的遥测信号可被耦合到偶极天线238上的调制信号，以启动或禁用生成用于发射到外部(或远程植入的)脉冲发生器模块106所必须的对应RF突发的波形。天线238可被连接到与组织接触的电极254，以为所发射的信号提供返回路径。A/D(未示出)转换器可用于将所存储的数据转化成能够在来自无线刺激器装置114的内部天线238的脉冲-调制信号上传输的序列化模式。
来自被植入无线刺激器装置114的遥测信号可包括刺激参数，比如从电极传递到组织的电流的功率或振幅。反馈信号可被发射到RF脉冲发生器模块116，以指示在神经束处的刺激的强度，通过将该信号耦合到被植入RX天线238，RX天线238辐射遥测信号至外部(或远程植入的)RF脉冲发生器模块106。反馈信号可包括模拟的和数字的遥测脉冲调制载体信号之一或两者。诸如刺激脉冲参数以及所测量的刺激器性能的特征的数据可被存储在被植入刺激器装置114内的内部存储装置中，并且被发送到遥测信号上。载体信号的频率可在300MHz至8GHz的范围内(优选在约700MHz和5.8GHz之间并且更优选在约800MHz和1.3GHz之间)。
在反馈子系统212中，遥测信号可利用解调器222向下行调制，并且通过模拟至数字(AD)转换器220进行处理而被数字化。然后，数字遥测信号可被路由到CPU 230，所述CPU230带嵌入码、带有重新编程的选项，以基于所接收的信号的振幅将该信号翻译成该组织中的对应电流测量结果。控制器子系统214的CPU 230可以使报告的刺激参数与保持在本地存储器228中的那些相比较，来验证无线刺激器装置114传递到组织的特定刺激。例如，如果无线刺激装置报告电流比指定的低，则来自RF脉冲发生器模块106的电流可被增大，以使被植入无线刺激器装置114具有更大的可用功率用于刺激。被植入无线刺激器装置114可实时生成遥测数据，例如，以每秒8千字节的速率。从被植入刺激器装置114接收的所有反馈数据可按照时间进行记录，并且被取样进行存储以被能够由健康护理人员访问的遥控监测系统取用用于进行趋势研究和分析相互关系。
被内部天线238接收的可远程编程的RF信号序列可被调理成波形，所述波形在可植入无线刺激器装置114内通过控制子系统242控制并且被路由至靠近待刺激组织设置的适当电极254。例如，从RF脉冲发生器模块106发射的RF信号可被RX天线238接收，并且通过被植入无线刺激器装置114内的电路、比如波束调理电路240处理而被转换成电脉冲，所述电脉冲通过电极接口252应用到电极254。在一些实施方式中，被植入无线刺激器装置114包含两个至十六个之间的电极254。
波束调理电路240可包括整流器244，所述整流器整流RX天线238接收的信号。经整流的信号可被馈送到控制器242用于接收来自RF脉冲发生器模块106的编码指令。整流器信号也可被馈送到电荷平衡部件246，所述电荷平衡部件被配置用于制造一个或多个电脉冲使得所述一个或多个电脉冲在所述一个或多个电极处生成大致零净电荷(也就是，脉冲被电荷平衡)。被电荷平衡的脉冲经过限流器248传递至电极接口252，其根据需要将脉冲应用到电极254。
限流器248确保了被应用到电极254的脉冲的电流水平不高于临界电流水平。在一些实施方式中，被接收的RF脉冲的振幅(例如，电流水平、低压水平、或功率水平)直接决定刺激的振幅。在这种情况下，包括限流器248来防止过高电流或电荷被传递通过这些电极可能是特别有利的，虽然在其它实施方式中限流器248可以使用，而在本实例中不是这种情况。一般来说，对于具有若干平方毫米表面积的给定电极来说，为安全起见应该被限制的是每相的电荷数(其中，刺激相所传递的电荷是电流的积分)。但是，在一些情况下，该限制可以放置在电流上，其中最大电流乘以最大可能的脉冲持续时间小于或等于最大安全电荷。更一般地，限制器248用作限制电脉冲特征(例如，电流或持续时间)的电荷限制器，以使每相的电荷数保持低于临界水平(典型地，安全电荷极限)。
在被植入无线刺激器装置114接收足以产生超过预定安全电荷极限的刺激的RF功率“强”脉冲的情况下，限流器248可自动限制或“剪断”刺激相以将相的总电荷维持在安全极限内。限流器248可以是一旦达到安全电流极限(临界电流水平)即切断至电极254的信号的无源电流限制件。可选地或附加地，限流器248可与电极接口252通信以断开所有电极254，防止破坏组织的电流水平。
剪断事件可以触发限流器反馈控制模式。剪断的动作可导致控制器向脉冲发生器106发送临界功率数据信号。反馈子系统212检测到临界功率信号并且将该信号解调成被通信至控制器子系统214的数据。控制器子系统214算法可以通过特别地降低RF脉冲发生器产生的RF功率或完全切断功率而在此电流限制环境发挥作用。以这种方式，如果被植入无线刺激器装置114报告其正在接收过高RF功率则脉冲发生器106可降低被传递至身体的RF功率。
刺激器205的控制器250可与电极接口252通信，用于控制电极设置的各方面以及被应用到电极254的脉冲。电极接口252可用作多路并且控制每一个电极254的极性和开关。例如，在一些实施方式中，无线刺激器106具有与组织接触的多个电极254，并且，对于给定的刺激来说，RF脉冲发生器模块106可以通过以参数指令无线地发送分派讯息来任意分派一个或多个电极1)用作刺激电极，2)用作回流电极，或3)停用，该控制器250根据需要利用所述参数指令设置电极接口252。例如，在生理学上来说可能有利的是分派一个或两个电极作为刺激电极并且分派所有剩余的电极作为回流电极。
而且，在一些实施方式中，对于给定的刺激脉冲来说，控制器250可以控制电极接口252，以在被指定的各刺激电极中任意分割电流(或根据来自脉冲发生器模块106的指令)。此对电极分派的控制和电流控制可能是有利的，因为实际上电极254可能沿着不同的神经结构空间地分配，并且，通过对刺激电极位置的战略性选择以及为每一个位置指定的电流比例，组织中的总体电流分布可被修改，以选择性地激活特定神经目标。此电流控制策略可提高患者的治疗效果。
在另一实施方式中，刺激的时间进程可被任意操控。给定的刺激波形可在时刻T_start开始并且在时刻T_final结束，此时间进程可被横跨所有刺激电极和回流电极同步；此外，此刺激循环的重复频率可以对于所有电极同步。然而，控制器250，独立地或响应于来自脉冲发生器106的指令，能够控制电极接口252以指定一个或多个电极子集以非同步的开始和停止时间传递刺激波形，并且每一个刺激循环的重复频率可被任意且独立地指定。
例如，具有八个电极的刺激器可被配置为具有五个电极构成的一子集，被称为集合A，和三个电极构成的一子集，被称为集合B。集合A可被配置为使其电极中的两个用作刺激电极，剩余的用作回流电极。集合B可被配置为仅具有一个刺激电极。然后，控制器250指定集合A传递3mA的刺激相、持续时间为200us，然后是电荷平衡相持续时间为400us。此刺激循环可被指定以每秒60个循环的速率重复。然后，对于集合B，控制器250可指定1mA电流的刺激相、持续时间为500us，然后是电荷平衡相持续时间为800us。集合B的刺激循环的重复速率可独立于集合A设置，例如可以指定每秒25个循环。或者，如果控制器250被配置为使集合B的重复速率匹配至集合A，那么，对于这种情况，控制器250可以指定刺激循环的相对开始时间在时间上同时进行或从彼此随意偏置某一延迟间隔。
在一些实施方式中，控制器250可任意成形刺激波形振幅，并且可以响应于来自脉冲发生器106的指令进行。刺激相可通过恒流源或恒压源进行，并且这种类型的控制可产生静态不变的特征波形，例如恒流源产生特征矩形脉冲，其中电流波形具有非常急剧的上升、用于刺激持续的恒定振幅、以及之后非常急剧地返回到基线。可选地或附加地，控制器250能够增大或减小在刺激相期间和/或在电荷平衡相期间任一时刻的电流水平。因此，在一些实施方式中，控制器250可传递任意成形的刺激波形，比如三角形脉冲、正弦脉冲、或高斯脉冲，例如。类似地，电荷平衡相可被任意地振幅成形，并且也可以振幅成形为领先的阳极脉冲(在刺激相之前)。
如上所述，无线刺激器装置114可包括电荷平衡部件246。一般来说，对于恒流刺激脉冲来说，脉冲应通过使阴电流的量值等于阳电流的量值而进行电荷平衡，这通常称为双相刺激。电荷密度是电流的量值乘以其被应用的持续时间，并且通常用单位uC/cm2表示。为了避免诸如pH变化的不可逆电化学反应、电极溶解以及组织破坏，在电极-电解质界面处不应出现净电荷，电荷密度小于30uC/cm2一般来说是可接受的。双相刺激电流脉冲确保了在每一个刺激循环之后没有净电荷出现在电极处，并且电化学过程被平衡以防止纯直流电流。无线刺激器装置114可被设计用于保证所生成的刺激波形具有零净电荷。通过减少或消除在电极-组织分界面处形成的电化学反应产物，电荷平衡的刺激被认为对组织具有最小破坏效果。
刺激脉冲可具有负电压或电流，被称为波形的阴极相。刺激电极在刺激循环期间的不同时刻可具有阴极相和阳极相两者。传递振幅足以刺激相邻神经组织的负电流的电极被称为“刺激电极”。在刺激相期间，刺激电极用作电流吸收器。一个或多个另外的电极用作电流源并且这些电极被称为“回流电极”。回流电极设置在距刺激电极某一距离处的、组织中的其它地方。当典型的负刺激相被在刺激电极处传递到组织时，回流电极具有正刺激相。在随后的电荷平衡相期间，每一个电极的极性被颠倒。
在一些实施方式中，电荷平衡部件246利用与刺激电极和身体组织串联电设置的隔直流电容器，其位于在刺激器电路内的刺激产生点和刺激传递至组织的位置点之间。以这种方式，可形成阻容(RC)网络。在多电极刺激器中，对于每一个电极可使用一个电荷平衡电容器或者在刺激器电路内、在电极选择点之前可使用集中式电容器。RC网络可阻挡直流电(DC)，然而它还可以阻止低频交流电(AC)被传递到组织。低于一截止频率，串联RC网络会从根本上阻挡信号，并且在一个实施例中，刺激器系统的设计可以确保截止频率不高于刺激波形的基频。在如这里描述的本实施例中，无线刺激器可具有电荷平衡电容器，其具有根据所测量的电极串联电阻和植入该刺激器的组织环境来选择的数值。在本实施例中，通过选择特定的电容值，RC网络的截止频率为刺激脉冲的基频或之下。
在其它实施方式中，截止频率可被选择为该刺激的基频或之上，并且，在此情景下，在电荷平衡电容器之前制造的刺激波形被称为驱动波形，其可被设计为非平稳的，其中驱动波形的包络在驱动脉冲的持续时间期间变化。例如，在一个实施例中，驱动波形的初始振幅被设定为初始振幅Vi，并且在脉冲的持续时间期间本振幅增加，直到其到达最终值k*Vi。通过随时间改变驱动波形的振幅，经过电荷平衡电容器的刺激波形的形状也被修改。刺激波形的形状可以此方式修改以便制造在生理学上有利的刺激。
在一些实施方式中，无线刺激器装置114可制造遵循由接收偶极天线238接收的RF脉冲的包络的驱动波形包络。在这种情况下，RF脉冲发生器模块106可直接控制无线刺激器装置114内驱动波形的包络，因而在刺激器自身内不需要能量存储装置。在本实施方式中，刺激器电路可以修改驱动波形的包络或可以将其直接传递至电荷平衡电容器和/或电极选择平台(stage)。
在一些实施方式中，被植入无线刺激器装置114可传递单相驱动波形至电荷平衡电容器或者它可以传递多相驱动波形。在单相驱动波形、例如负向矩形脉冲情况下，脉冲包括生理学刺激相，并且电荷平衡电容器在此相期间被极化(充电)。在驱动脉冲结束之后，电荷平衡功能完全由电荷平衡电容器的被动放电进行，其以相对于前面的刺激相反的极性穿过组织散尽其电荷。在一个实施方式中，刺激器内的电阻器有助于电荷平衡电容器的放电。在一些实施方式中，利用被动放电阶段，电容器可在后面的刺激脉冲开始之前允许差不多完全放电。
在多相驱动波形情况下，无线刺激器可进行内部切换以传递负向的或正向的脉冲(相)到电荷平衡电容器。这些脉冲可以任何序列以及以变化的振幅和波形形状传递，以实现预期的生理学效果。例如，刺激相之后可以是主动驱动的电荷平衡相，和/或在刺激相之前可以是相反相。在该刺激之前具有相反极性相，例如，可以具有减小用于刺激组织所需的刺激相振幅的优势。
在一些实施方式中，刺激和电荷平衡相的振幅和定时通过来自RF脉冲发生器模块106的RF脉冲的振幅和定时控制，并且在其它实施方式中此控制可以通过无线刺激器装置114自身携带的电路、比如控制器250内部管理。在自身携带方式控制的情况下，振幅和定时可以通过从脉冲发生器模块106传递的数据命令指定或修改。
在一些应用中，发射天线110可紧密靠近接收天线238放置。例如，发射天线110可由患者佩戴。在其它例子中，发射天线110可放置成更远离患者(以及容置着接收天线238的被植入无源神经刺激器)。在前一情况下，较少的能量可被从远程天线发射出，以向无源神经刺激器无线地提供功率和刺激参数设置。在一些场景中，患者可保持固定不动或睡着。在睡觉期间，患者可能不想佩戴通过缆线连接到控制器模块(比如控制器子系统214)的发射天线110。天线组件可被用于远程提供功率和刺激参数设置至无源神经刺激器。在本例子中，天线组件可以距被植入患者体内的无源神经刺激器大于10厘米。如果患者可以在房间四周移动；那么整个房间可能需要用微波能量场照射。在此情形下，天线的阵列、或宽波束天线可被使用。一些实施方式可引入可调控(例如，机械地，电地)的天线布置，包括接收天线位置跟踪系统。这些实施方式可进一步应用发射天线110的运动控制，以调节天线的照射角度或定向，使其指向接收天线的方向。输出功率根据需要、根据发射天线和接收天线之间的距离以及发射天线的指向性进行调节。
图3A-3C示出RF刺激系统的操作的例子。这些例子可引入单一远程发射天线或发射天线阵列。在一些例子中，该阵列可以是可调控的以聚焦到特殊位置上。在其它例子中，发射天线可以是固定的。
在图3A中，被植入有神经刺激器装置114的患者304在床306上休息，同时从发射天线系统302(例如，发射天线110和控制器子系统214)接受疗法。如图示，发射天线系统302被放置在同一房间中的其它地方，用于向被植入神经刺激器装置114发射包括功率和刺激参数的电磁能308。例如，远程发射天线系统302可放置在外科手术助手310身上或患者床附近的床头柜上。远程发射天线310系统可以是电池或墙上的电源。远程发射天线系统310可通过实体按钮(或控制器子系统214上的其它触碰用户界面)手动地、或通过无线指令协议比如Bluetooth或RF(例如，cellular，Wi-Fi等)从编程模块(未示出)接收编程或治疗指令。患者304可通过实体按钮或Bluetooth控制远程发射天线系统302。
图3B描绘了在没有可佩带天线系统的情况下发射电磁能308以向被植入神经刺激器装置114远程提供功率和刺激器参数同时患者304站立或四处走动的场景。在图示中，发射天线系统302(例如，发射天线110和控制器子系统214)设置在与站立或走动的患者在同一房间中的任意家具320上。
图3C描绘了带有被植入神经刺激器装置114的患者304背离发射天线系统302(例如，发射天线110和控制器子系统214)坐着的另一类似场景。例如，患者304可坐在办公椅上。在本图示中，电磁能308被从发射天线系统302发射出以向被植入神经刺激器装置114远程提供功率和刺激参数。
图4A示意出射线空间区域404在从远程发射天线系统302发射时的俯视图。更具体地，远程发射天线系统302的范围被图示为大致锥形和定向的，在远离远程发射天线系统302的一个方向上延伸。一般来讲，患者406可能需要停留在该射线空间区域内，来接收预期的刺激疗法。该空间区域可与站着或坐着的患者相互作用(即，远程发射天线系统可被配置为与在距远程天线给定距离和有效角度内的被植入天线相互作用)。
图4B示意出射线空间区域404在从远程发射天线系统302产生时的侧视图和三维图。在本图示中，系统射线空间区域404可覆盖在有效角度/距离内站立的患者406，以在患者站立时在被植入神经刺激器装置114上的接收天线处产生有效电场。
在这些图示中，功率和刺激参数的无线发射总体上通过视线操作。换句话说，发射天线系统302大致发射电磁辐射通过自由空间然后进入人体和被植入神经刺激器装置114内。阻挡的物体，比如带有导电损耗材料(例如，低介电常数)或反射RF的材料、比如金属，可能负面影响无线发射。
在这些图示中，发射天线系统302的位置可被调节以使发射天线系统302的辐射表面距被植入神经刺激器装置不小于一英尺。在此配置中，对于患者来说发射天线系统302可能不能是可穿戴设备。发射天线系统302的位置也可被调节为使得发射天线系统302的辐射表面距被植入神经刺激器装置不大于六英尺，以便可植入神经刺激器装置从发射天线系统302无线地接收足够的操作能量。发射天线系统302可以辐射极化电磁能，并且发射天线系统302的发射天线的定向可被调节以使发射天线与可植入神经刺激器装置上的接收天线更好地对准。当该对准通过重新定向而改进时，在接收天线处接收的电磁能也能够增加。
总体上参考图5A-5B，示出了UWB天线(例如，用于远程发射天线系统302)的总体设计。如图所示，远程发射天线系统302包括包围具有辐射表面504和馈入端口502的天线的矩形孔隙波导506。馈入端口502可包括用于耦合到缆线的缆线连接器508。示例性连接器可包括BNC(Bayonet Neill-Concelman)连接器或SMA(SubMiniature version A)连接器。
在本例子中，天线的辐射表面504是蝶形形状的。除两个叶结构504C1和504C2之外，此蝶形形状还包括连接这两个叶结构的两个杆结构504A和504B。蝶形辐射表面504具有连接波导506的接触件504C和504D。蝶形天线在波导506中分布电磁场并且诱导例如沿着杆结构504A和504B的长轴极化的波导传播模式。蝶形天线可在类似偶极子的宽带宽上辐射。用波导506包围天线改进了天线的指向性。将天线尺寸缩放比例可以确定天线的带宽。在一个实施方式中，天线尺寸可被缩放比例使得天线被参数化为具有从500MHz至4GHz的带。缩放比例可被简化至仅仅矩形波导内部的长度、宽度、和高度。
天线的优化尺寸的一个例子在下面的表1中给出了：
| 优化的UWB天线尺寸 | 数值(单位) |
| 波导(内部)的长度 | 30【cm】 |
| 波导(内部)的宽度 | 15【cm】 |
| 波导(内部)的高度 | 10.03【cm】 |
表1：参数化后的UWB天线示例尺寸
波导尺寸可随着蝶形天线的操作频率成比例变化。本文中，每个波导具有截止频率，超出了该频率波导便不能支持波的传播。当波导包围发射天线时，例如如图所示的蝶形天线，波导需要足够大以支持来自发射天线的电磁波的传播。然而，对于在图3A-3C中绘示的应用来说紧凑的发射天线系统是有利的。
如这里绘示的蝶形天线组件在尺寸上可小于在同一频率上操作的喇叭天线。在一些例子中，蝶形天线组件比在同一频率上操作的喇叭天线小2至3的因子。除波导横截面和总长度减小了之外，蝶形天线组件的指向性也可得到控制。在一些例子中，天线从波导的嘴口开始并且在辐射表面上可包括被制成锥形的介电过渡部。此锥形部在嘴口处可匹配波导，从而减少至馈入端口508的向回反射。此锥形还可以通过在空间上缩窄蝶形天线的主束宽而聚焦蝶形天线的主束。例如，在一个空间尺寸上缩窄能够致使所发射的电磁束在相同尺寸上的带宽缩窄。
下面示出了超宽带(UWB)天线的设计，同时通过建模进行了分析。在理论结果和从原型得到的实际测量结果之间具有强烈的相互关系，从而证明了仿真模型的精确度和可信性。一般来说，背后带腔的矩形孔隙天线(CB-RAA，如这里所使用的)具有使它们自身完美适合于远程天线应用的性能特征。CB-RAA可拥有用于在宽带上辐射的辐射特征。此外，其辐射效率非常接近圆形孔(81％对83.6％)，同时CB-RAA的电场线是平行的，因而在发射偏离发射天线110的瞄准线时提高了交叉极化性能。
用于UWB天线的这些特征可被引入到在这里讨论的发射天线110中。有利的是远程发射天线110是定向的、高效的、且深至远处的天线，所有这些都相对简单且容易制造。用于发射天线110的交叉极化和E-场定向可允许天线放置在一定范围内的位置，使得足够的能量到达被植入天线以启动该天线。与波导和聚焦透镜的添加相关联的大带宽响应可允许发射天线110精调至特殊频率，从而使天线更加能够在不同的特殊频率下操作。
参考图6A-6C，示出了带有波导的天线组件的例子。在图6A-6B中，侧板被除去以暴露出天线组件的内部结构，包括带有蝶形辐射表面以及被耦合到缆线连接器的馈入端口的发射天线110。图6C描绘出完整的天线组件(没有除去侧壁)。尺寸与目标天线模型(在表1中示出的)的尺寸的匹配在±0.5mm的公差内。
图7示意出HFSS模型(从有限元求解器)和图6的天线组件的原型在感兴趣的频带上的回波损耗的比较。回波损耗的特征在于由于天线的阻抗不匹配而导致的反射能的量。较多的反射损耗表示更加有效的功率传输。如图7中所示，用于回波损耗的模拟值和实际测量值两者都大致小于或等于-5dB。实际测量的原型值在500MHz和1.25GHz之间的频率上紧密匹配或改进了建模结果。
图8示出以915MHz的共振频率设计的天线组件的模拟回波损耗特征的例子。如图所示，根据需要反射缺口发生在915MHz处，那么蝶形天线参数化至915MHz。
图9A-9B示出模拟的来自图8的天线组件的电磁辐射图的例子。这些图对应于参数化的蝶形天线在共振(915MHz)时的总远场辐射图。在图9A中，该图是对蝶形天线并且没有波导的情况下计算得到的。在此结构中，蝶形天线围绕着极化轴线均匀地辐射。为了改进发射天线110的指向性，矩形波导可布置在蝶形天线的周围。图9B示出蝶形天线在共振(915MHz)时并且具有矩形孔隙波导的情况下在远场辐射图中所证明的改进的指向性。如图示，能量被集中在凸角上，如波导的孔隙所引导的。因此，在蝶形天线周围添加波导根据需要极大地增加了天线的指向性。在一些情况下，束宽可被矩形波导减小50％或以上。然而，由于波导的截止频率引起的频率成形，回波损耗、以及阻抗匹配可减小。为了缓和其下侧，波导的嘴口可提供被制成锥形的介电(例如，Dk＝3)圆顶部。
现在参考图10，介电圆顶部1006安装在波导孔隙1004的嘴口处并且覆盖辐射表面1002。在这种结构中，圆顶部1004用作天线嘴口处的聚集透镜。添加介电圆顶部1006以充填波导并且覆盖波导的嘴口可为蝶形天线的设计提供若干好处，例如，包括将没有介电充填物的矩形波导的回波损耗截止频率降低至915MHz以下，使得矩形波导的尺寸可进一步减小。此外，介电圆顶部在被制成锥形时可使所发射的能量在空间上缩窄，从而发射变得更集中。例如，在一个尺寸上被制成锥形的介电圆顶部可致使被辐射电磁波的束宽在相同尺寸上变窄。
圆顶部可以具有简单的半周期正弦或高斯形状，例如，沿着Y方向(虽然沿着X-方向的曲线分布可以保持常数)。如上面所讨论的，天线组件可诱导被沿着X方向(沿着杆结构1002A和1002B的长轴的方向)极化的波导发射模式图。显著地，被成形的介电圆顶部可在蝶形天线的上方和下方充填波导。然而，形状或轮廓的变化仅从波导的嘴口延伸，如图示。形状或轮廓的变化-如图示在本示例中为沿着Y方向-可有助于使所发射的电磁能在其向前传播时的散布减少。
圆顶部的高度-Hdome-可被配置用于改进S11(回波损耗)和S21(发射损耗)。圆顶部的高度是指从波导的嘴口延伸到圆顶部的顶点的高度。在一些实施方式中，高度可从0.5英寸变化到6英寸，取决于介电常数，介电常数可从1.5变化到9。对于915MHz的操作来说，介电的圆顶部的高度被选择为3英寸。
如图示，L表示波导的长度并且在从2.5cm至10cm的范围内变化。Hbowtie是指蝶形的高度位置并且可以固定在L/2处。在本图示中，“a”表示波导基部的较短侧向尺寸，其可以在从3.75cm至7.5cm的范围内变化，“b”表示波导基部的较长侧向尺寸，其可以在从7.5cm至15cm的范围内变化。选择特定的介电常数可以减小波导的尺寸。介电常数也可以帮助从金属波导释放电磁波，因而用作缓冲器来减少馈入端口处的反射。馈入端口可经由如上面所讨论的多种连接器(例如，BNC，SMA等)耦合到50ohm同轴电缆。
图11A-11B示出了图10的天线组件的模拟回波损耗和发射特征。在图11A中，对于一定范围的圆顶部高度来说，回波损耗被绘制为频率的函数。特别地，图示的回波损耗是与在915MHz下操作并且被间隔开1英寸的两个偶极天线的基线回波损耗相比的相对回波损耗。参数化(即，调节系统参数进行设计)的结果显示三英寸以及更大的圆顶部高度产生良好的匹配。然而，对于回波损耗中相对小收益的尺寸权衡显示高于三英寸仅有边际收益。因此，三英寸可被认为是具有可接受的反射损耗的最小高度，因此是可取的圆顶部高度。
图11B示出了对于一定范围的圆顶部高度的模拟发射损耗与频率。发射损耗是所发射的电磁波的衰减的特征。较大的数值(较小的负值)对应于较好的发射损耗和更高效的天线。当圆顶部高度高于三英寸时发射损耗中的增益在减小。显著地，发射损耗可以用作远程发射天线的特性的互补量度。因此，将圆顶部的高度制造成大于3英寸可得到非常小的收益。
参数化之后，尺寸可被明智地确定。用于915MHz的尺寸的例子在表2中给出了。反射和发射损耗曲线说明本设计得到了实质上的改进，用于本公开目的，但是为了进一步验证这些结果，可以检查在接收器处电场相互作用的等高线(contour)和远场辐射图。下面在表2中示出的波导尺寸随着蝶形天线的尺寸(如在上面表1中所示)成比例变化。
| 优化的远程天线尺寸 | 数值(单位) |
| 波导(内部)的长度 | 15.0【cm】 |
| 波导(内部)的宽度 | 7.6【cm】 |
| 波导(内部)的高度 | 5.0【cm】 |
表2：参数化后的最终远程天线尺寸
图12示出了来自图10的天线组件的模拟电磁辐射图的立体图。特别地，图12示出了根据表2的远程天线设计在915MHz时的远场辐射图。介质加载波导进一步改进了天线的指向性，用于提供传递至被植入神经刺激器装置的足够能量。远场图显示附加的介质加载进一步改进了指向性，这证实了前面发现的损耗特征以及E-场传播结果。另外，该图量化了天线相对于被植入神经刺激器装置的空间定向变化。结果证明被植入神经刺激器可以在远程发射天线的中心轴线的15°内并且仍接收所发射能量的一大部分。
图13A-13B示出了图12的模拟电磁辐射图的X-Z和Y-Z平面图。接收器天线1304是这两个平面的顶部部分。等高线示出与接收器天线1304相互作用的电磁能的前移凸角。这些图显示发射天线1302和接收器天线1304良好地耦合到一起，因为发射天线1302指向包括接收器天线1304的植入体，并且能量被高效地传递到植入体。由于所进行的进一步参数化，在915MHz时的远场辐射图得以改进，如上面所讨论的。
已经描述了许多实施方式。然而，应理解可制造许多修改。相应地，其它实施方式在下述权利要求的范围内。
Claims (6)
1.一种向可植入装置无线供应能量的方法，所述方法包括：
从天线组件上的辐射表面向所述可植入装置辐射电磁能，所述可植入装置被设置在至少10厘米远处，其中所述天线组件包括：
天线，所述天线包括具有所述辐射表面的金属信号层和馈入端口；和
波导，其包围天线并且被配置用于在远离天线的方向上引导从辐射表面发射的电磁能；和
控制器模块，其被连接到所述馈入端口并且被配置用于驱动天线以从辐射表面发射电磁能；
其中，所述辐射表面是蝶形的并且具有两个叶结构，所述两个叶结构在馈入端口处通过两个大致平行的杆结构连接到彼此，并且其中，所述天线、波导和控制器模块被构造成使得，当控制器模块驱动天线时，所发射的电磁能匹配可植入装置的接收特征并且足以使可植入装置仅仅利用从天线接收的电磁能即可制造振幅足以刺激患者的神经组织的一个或多个电脉冲。
2.根据权利要求1所述的方法，其中，辐射电磁能还包括在患者睡着时辐射电磁能，使得被制造的所述一个或多个电刺激脉冲在患者睡着期间被应用而刺激患者的神经组织。
3.根据权利要求1所述的方法，还包括：调节天线组件的位置使得天线组件的辐射表面距离可植入装置不大于六英尺。
4.根据权利要求1所述的方法，还包括：调节天线组件的位置使得天线组件的辐射表面距离可植入装置不小于一英尺。
5.根据权利要求1所述的方法，还包括：调节天线组件的定向使得在可植入装置处接收的被辐射电磁能增加。
6.根据权利要求1所述的方法，还包括：
建立编程模块至控制器模块之间的链接；和
从编程模块向控制器模块发射对将在可植入装置处制造以及随后被应用于刺激患者的神经组织的所述一个或多个刺激脉冲的参数编码的数据。
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| US (3) | US9409029B2 (zh) |
| EP (1) | EP3142743B1 (zh) |
| CN (2) | CN110665114B (zh) |
| AU (1) | AU2015259305B2 (zh) |
| IL (1) | IL248747B (zh) |
| WO (1) | WO2015175572A1 (zh) |
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| CN106794339A (zh) | 2017-05-31 |
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| AU2015259305B2 (en) | 2019-09-12 |
| US20160339258A1 (en) | 2016-11-24 |
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