CN104363849B - 具有开关的外科装置的控制电路以及用于确定开关状态的方法 - Google Patents
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Abstract
本发明公开了一种外科装置(1600)的控制电路(1602)。所述控制电路包括第一电路部分,所述第一电路部分联接到能够在打开状态和闭合状态之间进行操作的至少一个开关。所述第一电路部分通过导体对(112)与外科发生器(102)通信来接收控制信号以确定所述至少一个开关的状态。
Description
相关申请的交叉引用
本专利申请是2011年10月3日提交的名称为“SURGICAL GENERATOR FORULTRASONIC AND ELECTROSURGICAL DEVICES”的共同未决的美国专利申请序列号13/251,766的部分继续申请,该美国专利申请序列号13/251,766是2010年10月1日提交的名称为“SURGICAL GENERATOR FOR ULTRASONIC AND ELECTROSURGICAL DEVICES”的共同未决的美国专利申请序列号12/896,360的部分继续申请,该美国专利申请序列号12/896,360根据美国法典第35卷第119节(e)条要求于2009年10月9日提交的且名称为“A DUAL BIPOLAR ANDULTRASONIC GENERATOR FOR ELECTRO-SURGICAL INSTRUMENTS”的美国临时专利申请序列号61/250,217的权益。所述专利申请中的每一个据此全文以引用方式并入。
本专利申请还涉及同时提交于2011年10月3日的以下美国专利申请,所述专利申请中的每一个全文以引用方式并入本文:
(1)名称为“DEVICES AND TECHNIQUES FOR CUTTING AND COAGULATING TISSUE”、代理人案卷号为END6427USCIP1/080591CIP的美国专利申请序列号12/896,351;
(2)名称为“SURGICAL GENERATOR FOR ULTRASONIC AND ELECTROSURGICALDEVICES”、代理人案卷号为END6673USNP1/100557的美国专利申请序列号12/896,479;
(3)名称为“SURGICAL GENERATOR FOR ULTRASONIC AND ELECTROSU”RGICALDEVICES”、代理人案卷号为END6673USNP2/100559的美国专利申请序列号12/896,345;
(4)名称为“SURGICAL GENERATOR FOR ULTRASONIC AND ELECTROSURGICALDEVICES”、代理人案卷号为END6673USNP3/100560的美国专利申请序列号12/896,384;
(5)名称为“SURGICAL GENERATOR FOR ULTRASONIC AND ELECTROSURGICALDEVICES”、代理人案卷号为END6673USNP4/100562的美国专利申请序列号12/896,467;
(6)名称为“SURGICAL GENERATOR FOR ULTRASONIC AND ELECTROSURGICALDEVICES”、代理人案卷号为END6673USNP5/100563的美国专利申请序列号12/896,451;以及
(7)名称为“SURGICAL GENERATOR FOR ULTRASONIC AND ELECTROSURGICALDEVICES”、代理人案卷号为END6673USNP6/100564的美国专利申请序列号12/896,470。
背景技术
各种实施例涉及用于开放外科手术环境或微创外科手术环境的外科装置和发生器,该发生器用于将能量供应至外科装置。
超声外科装置(诸如超声手术刀)凭借它们的独特性能特性而在外科手术中得到日益广泛的应用。根据具体装置构型和操作参数,超声外科装置可通过凝固提供基本上同时的组织横切和体内平衡,从而有利地使患者创伤最小化。超声外科装置可包括容纳超声换能器的手持件和联接到超声换能器的器械,该器械具有远侧安装地用于切割并密封组织的端部执行器(例如,刀片顶端)。在一些情况下,该器械可永久性地附连到手持件。在其他情况下,正如在一次性器械或可在不同手持件之间互换的器械的情况下,该器械可从手持件拆卸。端部执行器将超声能量传输至与端部执行器接触的组织,以实现切割和密封动作。具有该性质的超声外科装置可能够用于开放性外科用途、腹腔镜式或内窥镜式外科手术,包括机器人辅助手术。
超声能量使用低于电外科手术中所使用温度的温度来切割和凝固组织,并且可通过与手持件连通的超声发生器传输至端部执行器。通过高频振动(例如,每秒55,500次),超声刀使组织中的蛋白变性以形成粘性凝固物。由刀片表面施加在组织上的压力使血管塌缩并允许所述凝固物形成止血密封。外科医生可通过由端部执行器施加至组织的力、施加力的时间以及端部执行器的选定偏移水平来控制切割速度和凝固。
超声换能器可被建模成包括第一支路和第二“动态”支路的等效电路,所述第一支路具有静态电容,所述第二“动态”支路具有串联的电感、电阻和电容,所述电感、电阻和电容限定谐振器的机电性能。已知的超声发生器可包括调谐电感器,所述调谐电感器用于使谐振频率下的静态电容失谐,使得基本上所有发生器的驱动信号电流均流入动态支路中。因此,通过使用调谐电感器,发生器的驱动信号电流表示动态支路电流,并且发生器因而能够控制其驱动信号以维持超声换能器的谐振频率。调谐电感器还可以转换超声换能器的相阻抗图,以改善发生器的频率锁定能力。然而,调谐电感器必须与处于操作谐振频率的超声换能器的特定静态电容相匹配。换句话讲,具有不同静态电容的不同超声换能器需要不同的调谐电感器。
另外,在一些超声发生器架构中,发生器的驱动信号显示使阻抗量值和相位测量复杂化的不对称谐波失真。例如,由于在电流和电压信号中存在谐波失真,所以阻抗相位测量的精确度可能下降。
此外,噪声环境中的电磁干扰降低发生器保持对超声换能器的谐振频率的锁定的能力,从而增加无效控制算法输入的可能性。
用于将电能施加至组织以治疗和/或破坏组织的电外科装置也在外科手术中得到日益广泛的应用。电外科装置可包括手持件和器械,该器械具有远侧安装地端部执行器(例如,一个或多个电极)的器械。所述端部执行器可抵靠组织定位,使得电流被引入组织中。电外科装置可能够用于双极性或单极性操作。在双极性操作期间,电流分别通过端部执行器的有源电极和返回电极被引入组织中并从组织返回。在单极性操作期间,电流通过端部执行器的有源电极被引入组织中,并通过返回电极(例如,接地垫)返回,所述有源电极与所述返回电极分开地位于患者身体上。流过组织的电流所产生的热可在组织内和/或在组织之间形成止血密封,并因此可尤其适用于密封例如血管。电外科装置的端部执行器还可包括能够相对于组织运动的切割构件以及用于横切组织的电极。
由电外科装置施加的电能可通过与手持件连通的发生器传输至器械。电能可为射频(“RF”)能的形式。射频能为可在300kHz至1MHz频率范围内的电能形式。在其操作过程中,电外科装置可穿过组织传输低频射频能,这引起离子振荡或摩擦,并实际上造成电阻加热,从而升高组织的温度。由于受影响的组织与周围组织之间可能形成明显的边界,所以外科医生能够以高精度水平进行操作,并在不损伤相邻的非目标组织的情况下进行控制。射频能的低操作温度可适用于移除、收缩软组织,或对软组织塑型,同时密封血管。射频能可以尤其良好地对结缔组织起作用,所述结缔组织主要由胶原构成并且在接触热时收缩。
由于具备独特的驱动信号、感测和反馈需求,所以超声和电外科装置通常具有需要的不同发生器。另外,在其中器械为一次性的或可与手持件互换的情形中,超声和电外科发生器识别所用特定器械构型以及相应地优化控制和诊断过程的能力受限。此外,发生器的非隔离电路和患者隔离电路之间的电容联接,尤其其中使用较高的电压和频率的情形中,可导致患者暴露于不可接受水平的漏电流。
此外,超声和电外科装置因其独特的驱动信号、感测和反馈需要而通常需要用于不同发生器的不同用户界面。在此类常规的超声和电外科装置中,一种用户界面能够与超声器械一起使用,而不同的用户界面能够与电外科器械一起使用。此类用户界面包括手启动和/或脚启动型的用户界面,诸如手启动型开关和/或脚启动型开关。当在后续公开内容中设想与超声和电外科器械一起使用的组合发生器的各种实施例时,也设想了能够与超声和/或电外科器械发生器一起操作的附加用户界面。
在后续公开内容内设想了为用户或其他机器提供反馈的附加用户界面,以提供指示超声和/或电外科器械中的任一者的操作模式或状态的反馈。提供用于操作组合型超声和/或电外科器械的用户和/或机械反馈将需要为用户提供感观反馈以及为机器提供电/机械/电-机械反馈。在后续公开内容内设想了用于组合的超声和/或电外科器械中的反馈装置,该反馈装置包括视觉反馈装置(例如,LCD显示屏、LED指示器)、听觉反馈装置(例如,扬声器、蜂鸣器)或触觉反馈装置(例如,触觉致动器)。
发明内容
本发明公开了将驱动信号传送至外科装置的发生器的各种实施例。根据各种实施例,发生器可包括功率放大器以接收时变驱动信号波形。可通过多个驱动信号波形样本的至少一部分的数模转换来生成驱动信号波形。功率放大器的输出可用于生成驱动信号。驱动信号可包括如下信号中的一种:将被传送至超声外科装置的第一驱动信号、将被传送至电外科装置的第二驱动信号。发生器还可包括采样电路以在将驱动信号传送至外科装置时生成驱动信号的电流和电压样本。该样本的生成可与驱动信号波形样本的数模转换同步,使得对于驱动信号波形样本的每次数模转换,采样电路均生成相应组的电流和电压样本。发生器还可包括至少一个装置,所述至少一个装置被程序设计为针对每个驱动信号波形样本和相应组的电流和电压样本将所述电流和电压样本存储在所述至少一个装置的存储器中,以将所存储样本与驱动信号波形样本相关联。所述至少一个装置还可被程序设计为当驱动信号包括第一驱动信号时:基于所存储电流和电压样本来确定超声外科装置的动态支路电流样本;将动态支路电流样本与靶样本进行比较,所述靶样本选自定义靶波形的多个靶样本,所述靶样本基于驱动信号波形样本进行选择;确定靶样本和动态支路电流样本之间的幅值误差;以及修改驱动信号波形样本使得在靶样本和后续动态支路电流样本之间确定的幅值误差减小,所述后续动态支路电流样本取决于与所修改驱动信号波形样本相关联的电流和电压样本。
根据各种实施例,发生器可包括存储器和联接到存储器的装置,所述装置针对用于合成驱动信号的多个驱动信号波形样本中的每一个来接收驱动信号的相应组的电流和电压样本。对于每个驱动信号波形样本和相应组的电流和电压样本,所述装置可将所述样本存储在其存储器中以将所存储样本与驱动信号波形样本相关联。另外,对于每个驱动信号波形样本和相应组的电流和电压样本,所述装置可在驱动信号包括将被传送至超声外科装置的第一驱动信号时,基于所存储样本确定超声外科装置的动态支路电流样本;将动态支路电流样本与靶样本进行比较,所述靶样本选自定义靶波形的多个靶样本,所述靶样本基于驱动信号波形样本进行选择;确定靶样本和动态支路电流样本之间的幅值误差;以及修改驱动信号波形样本以使得靶样本和后续动态支路电流样本之间确定的幅值误差减小,所述后续动态支路电流样本取决于与所修改驱动信号波形样本相关联的电流和电压样本。
根据各种实施例,本发明还公开了用于确定超声外科装置的超声换能器在换能器驱动信号的多个频率上的动态支路电流的方法。在一个实施例中,所述方法可包括在换能器驱动信号的多个频率中的每一个下,过采样换能器驱动信号的电流和电压;通过处理器接收电流和电压样本;以及由处理器基于电流和电压样本、超声换能器的静态电容和换能器驱动信号的频率来确定动态支路电流。
根据各种实施例,本发明还公开了用于控制外科装置的超声换能器中的动态支路电流的波形形状的方法。在一个实施例中,所述方法可包括通过使用直接数字合成(DDS)算法选择性地调用存储在查找表(LUT)中的驱动信号波形样本来生成换能器驱动信号;当将换能器驱动信号传送至外科装置时生成换能器驱动信号的电流和电压的样本;基于电流和电压样本、超声换能器的静态电容和换能器驱动信号的频率来确定动态支路电流的样本;将动态支路电流的每个样本与靶波形的相应靶样本进行比较以确定幅值误差;以及修改存储在LUT中的驱动信号波形样本,使得动态支路电流的后续样本和相应靶样本之间的幅值误差减小。
根据各种实施例,用于将驱动信号提供至外科装置的外科发生器可包括第一变压器和第二变压器。第一变压器可包括第一主线圈和第一次线圈。第二变压器可包括第二主线圈和第二次线圈。外科发生器还可包括发生器电路以生成驱动信号。发生器电路可电联接到第一主线圈以在整个第一主线圈上提供驱动信号。外科发生器还可包括与发生器电路电隔离的患者侧电路。患者侧电路可电联接到第一次线圈。另外,患者侧电路可包括第一输出线路和第二输出线路以将驱动信号提供至外科装置。此外,外科发生器可包括电容器。电容器和第二次线圈可串联地电联接在第一输出线路和地之间。
根据各种实施例,将驱动信号提供至外科装置的外科发生器可包括第一变压器、患者侧电路和电容器。第一变压器可包括主线圈、第一次线圈、和第二次线圈。第一次线圈相对主线圈的极性可与第二次线圈的极性相反。发生器电路可生成驱动信号并且可电联接到第一主线圈以在整个第一主线圈上提供驱动信号。患者侧电路可与发生器电路电隔离并且可电联接到第一次线圈。另外,患者侧电路可包括第一输出线路和第二输出线路以将驱动信号提供至外科装置。电容器和第二次线圈可串联地电联接在第一输出线路和地之间。
根据各种实施例,将驱动信号提供至外科装置的外科发生器可包括第一变压器、发生器电路、患者侧电路和电容器。第一变压器可包括主线圈和次线圈。发生器电路可生成驱动信号并且可电联接到第一主线圈以在整个第一主线圈上提供驱动信号。患者侧电路可与发生器电路电隔离并且可电联接到次线圈。另外,患者侧电路可包括第一输出线路和第二输出线路以将驱动信号提供至外科装置。电容器可电联接到主线圈和第一输出线路。
根据各种实施例,将驱动信号提供至外科装置的外科发生器可包括第一变压器、发生器电路、患者侧电路以及第一电容器、第二电容器和第三电容器。第一变压器可包括主线圈和次线圈。发生器电路可生成驱动信号并且可电联接到第一主线圈以在整个第一主线圈上提供驱动信号。患者侧电路可与发生器电路电隔离并且可电联接到次线圈。另外,患者侧电路可包括第一输出线路和第二输出线路以将驱动信号提供至外科装置。第一电容器的第一电极可电联接到主线圈。第二电容器的第一电极可电联接到第一输出线路并且第二电容器的第二电极可电联接到第一电容器的第二电极。第三电容器的第一电极可电联接到第一电容器的第二电极和第二电容器的第二电极。第三电容器的第二电极可电联接到地。
根据各种实施例,本发明还公开了外科装置的控制电路。在一个实施例中,控制电路可包括具有至少一个第一开关的第一电路部分。第一电路部分可通过导体对与外科发生器通信。控制电路还可包括具有数据电路元件的第二电路部分。数据电路元件可设置在外科装置的器械中并且可传输或接收数据。数据电路元件可通过导体对的至少一个导体实现与外科发生器的数据通信。
根据各种实施例,控制电路可包括具有至少一个第一开关的第一电路部分。第一电路部分可通过导体对与外科发生器通信。控制电路还可包括具有数据电路元件的第二电路部分。数据电路元件可设置在外科装置的器械中并且可传输或接收数据。数据电路元件可通过导体对的至少一个导体实现与外科发生器的数据通信。第一电路部分可接收从外科发生器以第一频带传输的第一询问信号。数据电路元件可使用以第二频带传输的调幅通信协议与外科发生器通信。第二频带可高于第一频带。
根据各种实施例,控制电路可包括具有至少一个第一开关的第一电路部分。第一电路部分可接收从外科发生器通过导体对传输的第一询问信号。控制电路还可包括第二电路部分,所述第二电路部分包括设置在所述装置的器械中的电阻元件和感应元件中的至少一个。第二电路部分可接收从外科发生器通过导体对传输的第二询问信号。第二电路部分可与第一电路部分频带分离。当通过第一电路部分接收到第一询问信号时,第一询问信号的特性可指示至少一个第一开关的状态。当通过第二电路部分接收到第二询问信号时,第二询问信号的特性可独特地识别所述装置的器械。
根据各种实施例,控制电路可包括具有第一开关网络和第二开关网络的第一电路部分。第一开关网络可包括至少一个第一开关,并且第二开关网络可包括至少一个第二开关。第一电路部分可通过导体对与外科发生器通信。控制电路还可包括具有数据电路元件的第二电路部分。数据电路元件可设置在外科装置的器械中并且可传输或接收数据。数据电路元件可通过导体对的至少一个导体与外科发生器进行数据通信。
根据各种实施例,用于将驱动信号提供至外科装置的外科发生器可包括具有孔的外科发生器主体。外科发生器还可包括定位在孔中的插座组件。插座组件可包括插座主体以及具有内壁和外壁的凸缘。内壁可由至少一个弯曲部分和至少一个线性部分构成。内壁可限定腔体。中央凸出部分可定位在腔体中并且可包括磁体和多个承窝。中央凸出部分的外周边可包括至少一个弯曲部分和至少一个线性部分。
根据各种实施例,外科器械可包括电连接器组件。电连接器组件可包括限定中央腔体的凸缘和延伸到中央腔体中的磁性相容引脚。电连接器组件可包括电路板和联接到电路板的多个导电引脚。多个导电引脚中的每一个均可延伸到中央腔体中。电连接器组件还可包括应变消除构件和防护罩。
根据各种实施例,外科器械系统可包括具有插座组件的外科发生器。插座组件可包括至少一个弯曲部分和至少一个线性部分。外科器械系统可包括具有连接器组件和适配器组件的外科器械,所述适配器组件操作地联接到插座组件和连接器组件。适配器组件可包括接触插座组件的远侧部分。远侧部分可包括凸缘,其中所述凸缘具有至少一个弯曲部分和至少一个线性部分。适配器组件可包括接触连接器组件的近侧部分。近侧部分可限定尺寸设定成接收连接器组件的至少一部分的腔体。适配器组件还可包括电路板。
根据各种实施例,可使用方法(例如,结合外科器械)来实现多个外科目的。例如,用于控制通过第一电极和第二电极提供至组织的电功率的方法可包括通过第一电极和第二电极将驱动信号提供至组织以及基于感测的组织阻抗并根据第一功率曲线来通过驱动信号调制提供至组织的功率。第一功率曲线可为多个可能感测的组织阻抗中的每一个定义第一相应功率。所述方法还可包括通过第一电极和第二电极监测提供至组织的总能量。当总能量达到第一能量阈值时,所述方法可包括确定组织的阻抗是否已达到第一阻抗阈值。所述方法还可包括如果组织的阻抗不能达到第一阻抗阈值,则基于感测的组织阻抗并根据第二功率曲线来通过驱动信号调制提供至组织的功率。第二功率曲线可为多个可能感测的组织阻抗中的每一个定义第二相应功率。
根据各种实施例,用于控制通过第一电极和第二电极提供至组织的电功率的方法可包括通过第一电极和第二电极将驱动信号提供至组织以及确定将被提供至组织的功率。所述确定可包括接收对感测的组织阻抗的指示;根据功率曲线来确定用于所感测的组织阻抗的第一相应功率;以及将相应的功率乘以乘数。功率曲线可为多个可能感测的组织阻抗中的每一个定义相应功率。所述方法还可包括调制驱动信号以将确定功率提供至组织,以及如果组织的阻抗不能达到第一阻抗阈值,则根据提供至组织的总能量来增加乘数。
根据各种实施例,用于控制通过第一电极和第二电极提供至组织的电功率的方法可包括通过第一电极和第二电极将驱动信号提供至组织以及确定将被提供至组织的功率。所述确定可包括接收对感测的组织阻抗的指示;根据功率曲线来确定用于感测的组织阻抗的第一相应功率;以及将相应功率乘以第一乘数以找到确定功率。功率曲线可为多个可能感测的组织阻抗中的每一个定义相应功率。所述方法还可包括调制驱动信号以将确定功率提供至组织以及通过第一电极和第二电极监测提供至组织的总能量。此外,所述方法可包括当总能量达到第一能量阈值时,确定组织的阻抗是否已达到第一阻抗阈值;以及如果组织的阻抗未达到第一阻抗阈值,则将第一乘数增加第一数量。
根据各种实施例,用于控制通过外科装置提供到组织的电功率的方法可包括:将驱动信号提供到外科装置;接收组织阻抗的指示;计算组织阻抗的增加速率;以及调制驱动信号,以将阻抗的增加速率保持为大于或等于预先确定的常数。
根据各种实施例,用于控制通过外科装置提供至组织的电功率的方法可包括提供驱动信号。驱动信号的功率可与通过外科装置提供至组织的功率成比例。所述方法还可包括周期性地接收组织阻抗的指示以及将第一复合功率曲线应用至组织,其中将第一复合功率曲线应用至组织包括。将第一复合功率曲线应用至组织可包括将第一预先确定数量的第一复合功率曲线脉冲调制到驱动信号上;以及对于第一复合功率曲线脉冲中的每一个,根据组织阻抗的第一函数来确定脉冲功率和脉冲宽度。所述方法还可包括将第二复合功率曲线应用至组织。将第二复合功率曲线应用至组织可包括将至少一个第二复合功率曲线脉冲调制到驱动信号上;以及对于至少一个第二复合功率曲线脉冲中的每一个,根据组织阻抗的第二函数来确定脉冲功率和脉冲宽度。
根据各种实施例,提供了用于为外科装置生成驱动信号的发生器。所述发生器包括用于生成第一驱动信号以驱动超声装置的超声发生器模块、用于生成第二驱动信号以驱动电外科装置的电外科/射频(RF)发生器模块、以及联接到超声发生器模块和电外科/射频发生器模块中的每一个的脚踏开关。当超声装置联接到超声发生器模块时,脚踏开关能够以第一模式操作,并且当电外科装置联接到电外科/射频发生器模块时,脚踏开关能够以第二模式操作。
根据各种实施例,提供了发生器,所述发生器包括用户界面以根据超声装置和电外科装置中任一者的操作并根据预先确定的算法来提供反馈。
根据各种实施例,提供了外科装置的控制电路。控制电路包括第一电路部分,该第一电路部分联接到能够在打开状态和闭合状态之间进行操作的至少一个开关。第一电路部分通过导体对与外科发生器通信来接收控制信号以确定所述至少一个开关的状态。
根据各种实施例,提供了外科装置的控制电路。控制电路包括第一电路部分,该第一电路部分联接到能够在打开状态和闭合状态之间进行操作的至少一个开关。第一电路部分通过导体对与外科发生器通信来接收来自输入端子的控制信号,以确定所述至少一个开关的状态。控制信号具有正相位和负相位。第一晶体管联接在输入端子和第一电容器之间,并且第一电阻器与第一电容器串联联接。在控制信号的正相位期间,当第一电容器充电至预先确定的电压时,第一晶体管保持在截止模式,并且在控制信号负相位的初始部分期间,第一晶体管从截止模式转变至饱和模式并保持在饱和模式,直至第一电容器通过第一电阻器放电。在控制信号负相位的最后部分期间,当第一电容器电压降至预先确定的阈值以下时,第一晶体管从饱和模式转变至截止模式。
根据各种实施例,提供了一种方法。所述方法包括在外科装置的控制电路处接收控制信号,并基于电阻器的值确定至少一个开关的状态。控制电路包括第一电路部分,该第一电路部分联接到能够在打开状态和闭合状态之间进行操作的至少一个开关。所述电路部分通过导体对与外科发生器通信来接收控制信号。第一电路部分包括联接到至少一个开关的至少一个电阻器。
附图说明
各种实施例的新型特征在所附权利要求书中具体地示出。然而,对组织和操作方法来讲均可通过结合附图参照以下描述最深刻地理解所描述的实施例,其中:
图1示出了包括发生器和可与发生器一起使用的各种外科器械的外科系统的一个实施例;
图2示出了可用于横切和/或密封的实例超声装置的一个实施例;
图3示出了图2的实例超声装置的端部执行器的一个实施例。
图4示出了也可用于横切和密封的实例电外科装置的一个实施例;
图5、图6和图7示出了图4中所示的端部执行器的一个实施例;
图8为图1的外科系统的图示;
图9为示出一个实施例中的动态支路电流的模型;
图10为一个实施例中的发生器架构的结构视图;
图11A-11C为一个实施例中的发生器架构的功能视图;
图12示出了在一个实施例中用于监测输入装置并控制输出装置的控制器;
图13A-13B示出了发生器的一个实施例的结构和功能方面;
图14-32和图33A-33C示出了控制电路的实施例;
图33D-33I示出了用于连接各种发生器和各种外科器械的缆线布线和适配器构型的实施例;
图34示出了用于漏电流的有源消除的电路300的一个实施例。
图35示出了可以通过图1的发生器实施的用于提供漏电流的有源消除的电路的一个实施例;
图36示出了可以通过图1的发生器实施的用于提供漏电流的有源消除的电路的另选的实施例;
图37示出了可以通过图1的发生器实施的用于提供漏电流的有源消除的电路的另选的实施例;
图38示出了可以通过图1的发生器实施的用于提供漏电流的有源消除的电路的另一个实施例;
图39示出了可以通过图1的发生器实施的用于提供漏电流的消除的电路的实施例;
图40示出了可以通过图1的发生器实施的用于提供漏电流的消除的电路的另一个实施例;
图41示出了一个实施例中的插座和连接器接口;
图42为一个实施例中的插座组件的分解侧视图;
图43为一个实施例中的连接器组件的分解侧视图;
图44为图41中所示的插座组件的透视图;
图45为一个实施例中的插座组件的分解透视图;
图46为一个实施例中的插座组件的前正视图;
图47为一个实施例中的插座组件的侧正视图;
图48为一个实施例中的承窝的放大视图;
图49为一个实施例中的连接器组件的透视图;
图50为一个实施例中的连接器组件的分解透视图;
图51为一个实施例中的连接器主体的侧正视图;
图52为一个实施例中的连接器主体的远端的透视图;
图53为一个实施例中的连接器主体的近端的透视图;
图54示出了一个实施例中的铁质引脚;
图55示出了一个实施例中的导电引脚和电路板;
图56示出了一个实施例中的应变消除构件;
图57示出了一个实施例中的防护罩;
图58示出了根据各种非限制性实施例的两个适配器组件;
图59示出了一个实施例中的外科发生器;
图60示出了一个实施例中的连接至适配器组件的连接器组件;
图61示出了一个实施例中的插入到外科发生器的插座组件中的适配器组件;
图62示出了一个实施例中的连接至适配器组件的连接器组件;
图63示出了一个实施例中的发生器的后面板的透视图;
图64示出了一个实施例中的发生器的后面板;
图65和图66示出了一个实施例中的发生器的后面板的不同部分;
图67示出了一个实施例中的用于控制发生器的神经网络;
图68示出了一个实施例中的测量温度与估计温度的对比图,所述估计温度由通过发生器控制的外科器械输出;
图69示出了显示实例功率曲线的图表的一个实施例;
图70示出了用于将一个或多个功率曲线应用到组织切口的处理流程的一个实施例;
图71示出了显示可结合图70的处理流程使用的实例功率曲线的图表的一个实施例;
图72示出了显示可结合图70的处理流程使用的实例同形功率曲线的图表的一个实施例;
图73A示出了可以通过图1的发生器的数字装置执行的作用于新组织切口的例程的一个实施例;
图73B示出了可以通过图1的发生器的数字装置执行的监测组织阻抗的例程的一个实施例;
图73C示出了可以通过图1的发生器的数字装置执行的将一个或多个功率曲线提供到组织切口的例程的一个实施例;
图74示出了用于将一个或多个功率曲线应用到组织切口的处理流程的一个实施例;
图75示出了描述通过图1的发生器选择和施加复合负载曲线的框图的一个实施例;
图76示出了显示如通过图1的发生器实施的图75的算法的一个实施例的处理流程;
图77示出了用于生成第一复合负载曲线脉冲的处理流程的一个实施例;
图78示出了脉冲时序图的一个实施例,所述脉冲时序图示出了图76的算法通过图1的发生器的实例应用;
图79示出了根据实例复合负载曲线的驱动信号电压、电流和功率的图形表示;
图80-85示出了实例复合负载曲线的图形表示;
图86示出了描述应用算法以用于保持恒定的组织阻抗变化速率的框图的一个实施例;
图87示出了控制电路的一个实施例,所述控制电路包括具有高速数据通信支持的并行切换电阻电路和包括至少一个存储器装置的至少一个数据元件。
图88为恒定电流脉冲波形形式的控制信号的一个方面的图形表示,所述恒定电流脉冲波形可由如图10中所示发生器的信号调节电路生成。
图88A为图88的恒定电流脉冲波形形式的控制信号的一个方面的图形表示,示出了根据一个示例性实施例的波形的各种特征的数值。
图89为与图88中示出的控制信号的该方面相关联的各种检测区域的图形表示。
图90为在SW1闭合且缆线/连接器阻抗为0欧姆的发生器处测量的电流脉冲波形形式的控制信号的一个方面的图形表示。
图90A为图90的电流脉冲波形形式的控制信号的一个方面的图形表示,示出了根据一个示例性实施例的波形的各种特征的数值。
图91为使用发生器和控制电路实际测量的模数(ADC)输入波形的示波器描迹。
图92示出了控制电路的另一个实施例,所述控制电路包括并行切换电阻电路和包括至少一个存储器装置的至少一个数据元件。
图93示出了控制电路的一个实施例,所述控制电路包括串行切换电阻电路和包括至少一个存储器装置的至少一个数据元件。
图94示出了控制电路的一个实施例,所述控制电路包括具有精密基准电压的串行切换电阻电路和包括至少一个存储器装置的至少一个数据元件。
图95示出了控制电路的一个实施例,所述控制电路包括可变频率切换电阻电路和包括至少一个存储器装置的至少一个数据元件。
图96为检测方法的一个实施例的图形表示,示出了用于控制电路的检测区域,所述控制电路如结合图95所述包括可变频率切换电阻电路和存储器装置。
图97示出了控制电路的一个实施例,所述控制电路包括具有精密基准电压的并行切换电阻电路和包括至少一个存储器装置的至少一个数据元件,所述存储器装置采用可变斜率波形来确定开关状态。
图98为检测方法的一个实施例的图形表示,示出了用于控制电路的检测区域,所述控制电路如结合图97所述包括可变斜坡/斜率切换电阻电路和存储器装置。
图99示出了包括单线多开关输入装置的控制电路的一个实施例。
具体实施方式
在详细说明外科装置和发生器的各种实施例之前,应该指出的是,示例性实施例的应用或使用并不局限于附图和具体实施方式中详细示出的部件的构造和布置。示例性实施例可单独实施,也可与其他实施例、变型和修改形式结合在一起实施,并可以通过各种方式实践或执行。此外,除非另外指明,否则本文所用的术语和表达是出于方便读者而对示例性实施例进行描述的目的选取的,并非出于限制的目的。另外,应当理解,下述实施例、实施例表达和/或实例中的一个或多个可与下述其他实施例、实施例表达和/或实例中的任何一个或多个结合。
各种实施例涉及改善的超声外科装置、电外科装置以及与它们一起使用的发生器。超声外科装置的实施例可能够用于例如在外科手术期间横切和/或凝固组织。电外科装置的实施例可能够用于例如在外科手术期间横切、凝固、剥落、吻合和/或干燥组织。
发生器的实施例使用发生器驱动信号电流和电压的高速模数采样(例如,大约200x过采样,这取决于频率)以及数字信号处理,从而与已知发生器架构相比提供多个优点和有益效果。在一个实施例中,例如,基于电流和电压反馈数据、超声换能器静态电容的值、和驱动信号频率的值,发生器可确定超声换能器的动态支路电流。这提供虚拟调谐系统的有益效果并模拟如下系统的存在,所述系统利用任何频率下的静态电容(例如,图9中的C0)的任何值进行调谐或谐振。因此,可通过使静态电容的效果失谐来实现动态支路电流的控制,且无需使用调谐电感器。另外,除去调谐电感器可不降低发生器的频率锁定能力,因为可通过适当地处理电流和电压反馈数据来实现频率锁定。
发生器驱动信号电流和电压的高速模数采样以及数字信号处理也可允许样本的精确数字滤波。例如,发生器的实施例可利用在基础驱动信号频率和第二级谐波之间衰减的低通数字滤波器(例如,有限脉冲响应(FIR)滤波器)以减少电流和电压反馈样本中的不对称谐波失真和EMI引起的噪声。经滤波的电流和电压反馈样本基本上表示基础驱动信号频率,由此能够相对基础驱动信号频率来进行更精确的阻抗相位测量以及改善发生器保持谐振频率锁定的能力。可通过如下方式进一步地提高阻抗相位测量的精确性:使下降沿和上升沿相位测量平均化以及将所测量的阻抗相位调节至0°。
发生器的各种实施例也可使用发生器驱动信号电流和电压的高速模数采样以及数字信号处理来高精度地确定真实功耗和其他数量。这可允许发生器实施多种可用算法,例如,控制当组织阻抗变化时递送至组织的功率量以及控制功率递送以保持组织阻抗增加的恒定速率。
发生器的各种实施例可具有宽频率范围以及驱动超声外科装置和电外科装置必需的增加的输出功率。可通过宽带功率变压器上的专用分接头来满足电外科装置的较低电压、较高电流需求,从而消除了对单独的功率放大器和输出变压器的需要。此外,发生器的感测和反馈电路可支持大动态范围,该大动态范围解决具有最小失真的超声和电外科应用两者的需要。
各种实施例可为发生器提供简单经济的装置以用于读取和任选地写入设置在如下器械中的数据电路(例如,单总线装置,诸如以商品名“1-Wire”为人所知的单线协议EEPROM),所述器械使用现有多导体发生器/手持件缆线附接到手持件。这样,发生器能够从附接到手持件的器械检索和处理器械专用数据。这可允许发生器提供较好的控制以及改善的诊断和误差检测。另外,发生器将数据写入所述器械的能力使以下方面的新功能成为可能,例如,跟踪器械用法以及捕获操作数据。此外,频带的使用允许容纳总线装置的器械与现有发生器的向后兼容性。
发生器的所公开实施例提供漏电流的有源消除,所述漏电流是由发生器的非隔离电路与患者隔离电路之间的非预期电容联接引起的。除了降低患者风险之外,减少漏电流还可降低电磁发射。
通过下文的具体实施方式,本发明的实施例的这些和其他有益效果将显而易见。
应当理解,相对于抓持手持件的临床医生而言,本文使用术语“近侧”和“远侧”。因此,端部执行器相对于较近的手持件而言处于远侧。还应当理解,为简洁和清楚起见,相对于抓持手持件的临床医生而言,本文也可使用诸如“顶部”和“底部”之类的空间术语。然而,外科装置在多个取向和位置中使用,并且这些术语并非意图进行限制,也并非绝对的。
图1示出外科系统100的一个实施例,该外科系统100包括能够与外科装置一起使用的发生器102。根据各种实施例,发生器102能够与不同类型的外科装置一起使用,所述外科装置包括例如超声外科装置104和电外科或射频外科装置106。虽然在图1的实施例中,发生器102被示为与外科装置104、106分开,但某些实施例中,发生器102可与外科装置104、106中的任一者一体形成,以形成一体式外科系统。
图2示出了可用于横切和/或密封的实例超声装置104的一个实施例。装置104可包括手持件116,所述手持件116又可包括超声换能器114。换能器114可例如经由缆线122(例如,多导体缆线)与发生器102电连通。换能器114可包括适于将驱动信号的电能转换成机械振动的压电陶瓷元件、或者其他元件或部件。当被发生器102启动时,超声换能器114可引起纵向振动。振动可通过装置104的器械部分124(例如,经由嵌入外部护套中的波导)传输至器械部分124的端部执行器126。
图3示出了实例超声装置104的端部执行器126的一个实施例。端部执行器126可包括可经由波导(未示出)联接到超声换能器114的刀片151。当被换能器114驱动时,刀片151可振动,并且当接触到组织时可切割和/或凝固组织,如本文所述。根据各种实施例,并且如图3所示,端部执行器126还可包括可能够用于与端部执行器126的刀片151协同作用的夹持臂155。结合刀片151,夹持臂155可包括一组钳口140。夹持臂155可枢转地连接在器械部分124的轴153的远端处。夹持臂155可包括可由或其他合适的低摩擦材料形成的夹持臂组织垫163。垫163可被安装用于与刀片151协作,其中夹持臂155的枢转移动将夹持垫163定位成与刀片151呈基本上平行关系并接触所述刀片。通过该构造,将被夹持的组织切口可被紧抓在组织垫163和刀片151之间。组织垫163可具有锯齿状构型(包括多个轴向间隔开的、朝近侧延伸的抓持齿161)以与刀片151协作来提高对组织的抓持。夹持臂155可从图3中所示的打开位置以任何合适的方式转变成闭合位置(其中夹持臂155接触或靠近刀片151)。例如,手持件116可包括钳口闭合触发器138。当被临床医生致动时,钳口闭合触发器138可以任何合适的方式来枢转夹持臂155。
发生器102可被启动以按任何合适的方式将驱动信号提供至换能器114。例如,发生器102可包括脚踏开关120,该脚踏开关120经由脚踏开关缆线122联接到发生器102(图8)。临床医生可通过压下脚踏开关120来启动换能器114,并由此启动换能器114和刀片151。此外,或作为脚踏开关120的替代,装置104的一些实施例可利用定位在手持件116上的一个或多个开关,当被启动时,所述一个或多个开关可使发生器102启动换能器114。在一个实施例中,例如所述一个或多个开关可例如包括一对开关按钮136a,136b,以确定装置104的操作模式。当开关按钮136a被压下时,例如,超声发生器102可将最大驱动信号提供至换能器114,从而使所述换能器产生最大超声能量输出。压下开关按钮136b可使超声发生器102将用户可选的驱动信号提供至换能器114,从而使所述换能器产生小于最大值的超声能量输出。除此之外或作为另外一种选择,装置104可包括第二开关以例如指示用于操作端部执行器126的钳口140的钳口闭合触发器138的位置。此外,在一些实施例中,超声发生器102可基于钳口闭合触发器138的位置被启动(例如,当临床医生压下钳口闭合触发器138以闭合钳口140时,可施加超声能量)。
除此之外或作为另外一种选择,所述一个或多个开关可包括开关按钮136c,当所述开关按钮被压下时,会使发生器102提供脉冲输出。脉冲例如可按任何合适的频率和分组提供。在某些实施例中,例如,脉冲的功率水平可为与开关按钮136a,136b相关联的功率水平(最大值、小于最大值)。
应当理解,装置104可包括开关按钮136a,136b,136c的任何组合。例如,装置104能够仅具有两个开关按钮:用于产生最大超声能量输出的开关按钮136a,以及用于产生最大功率水平或小于最大的功率水平下的脉冲输出的开关按钮136c。这样,发生器102的驱动信号输出构型可为5个连续信号和5或4或3或2或1个脉冲信号。在某些实施例中,例如可基于发生器102中的EEPROM设定和/或用户功率水平选择来控制特定的驱动信号构型。
在某些实施例中,可提供双位开关作为开关按钮136c的替代形式。例如,装置104可包括双位开关按钮136b和用于产生最大功率水平下的连续输出的开关按钮136a。在第一止动位置中,开关按钮136b可产生小于最大功率水平下的连续输出,并且在第二止动位置中,开关按钮136b可产生脉冲输出(例如,最大功率水平下或小于最大的功率水平下的脉冲输出,取决于EEPROM设置)。
在一些实施例中,端部执行器126还可包括一对电极159,157。电极159,157可例如经由缆线122与发生器102通信。电极159,157可用于例如测量存在于夹持臂155和刀片151之间的组织切口的阻抗。发生器102可将信号(例如,非治疗信号)提供至电极159,157。可例如通过监测信号的电流、电压等来发现组织切口的阻抗。
图4示出了也可用于横切和密封的实例电外科装置106的一个实施例。根据各种实施例,横切和密封装置106可包括手持件组件130、轴165和端部执行器132。轴165可为刚性的(例如,用于腹腔镜式和/或开放性外科应用)或柔性的,如图所示(例如,用于内窥镜式应用)。在各种实施例中,轴165可包括一个或多个关节运动点。端部执行器132可包括具有第一钳口构件167和第二钳口构件169的钳口144。第一钳口构件167和第二钳口构件169可连接至U形夹171,该U形夹171又可联接到轴165。平移构件173可在轴165内从端部执行器132延伸至手持件130。在手持件130处,轴165可直接或间接地联接到钳口闭合触发器142(图4)。
端部执行器132的钳口构件167,169可包括相应的电极177,179。电极177,179可经由电引线187a,187b连接至发生器102(图5),所述电引线从端部执行器132穿过轴165和手持件130并最终延伸至发生器102(例如,通过多导体缆线128)。发生器102可将驱动信号提供至电极177,179,以对存在于钳口构件167,169内的组织产生治疗效果。电极177,179可包括有源电极和返回电极,其中所述有源电极和所述返回电极可抵靠或邻近将被处理的组织定位,使得电流可从有源电极通过组织流至返回电极。如图4所示,端部执行器132被示为具有处于打开位置的钳口构件167,169。往复式刀片175示于钳口构件167,169之间。
图5、图6和图7示出了图4中所示的端部执行器132的一个实施例。为了闭合端部执行器132的钳口144,临床医生可使钳口闭合触发器142沿箭头183从第一位置枢转到第二位置。这可根据任何合适的方式使钳口144打开和闭合。例如,钳口闭合触发器142的移动又可引起平移构件173在轴165的镗孔185内平移。平移构件173的远侧部分可联接到往复式构件197,使得平移构件173的远侧运动和近侧运动引起往复式构件的相应远侧运动和近侧运动。往复式构件197可具有肩部191a,191b,而钳口构件167,169可具有相应的凸轮表面189a,189b。当往复式构件197从图6中所示的位置向远侧平移至图7中所示的位置时,肩部191a,191b可接触凸轮表面189a,189b,从而使钳口构件167,169转变成闭合位置。另外,在各种实施例中,刀片175可定位在往复式构件197的远端处。随着往复式构件延伸到图7中所示的完全远侧位置,刀片175可在该过程中推动穿过存在于钳口构件167,169之间的任何组织,从而切割该组织。
在使用中,临床医生可放置端部执行器132并且例如通过沿所述箭头183枢转钳口闭合触发器142以围绕将被作用的组织切口来闭合钳口144。一旦组织切口固定在钳口144之间,临床医生就可通过发生器102并穿过电极177,179开始提供射频或其他电外科能量。可以任何合适的方式来完成射频能量的提供。例如,外科医生可启动发生器102的脚踏开关120(图8)以开始提供射频能量。另外,例如,手持件130可包括可由临床医生致动以使发生器102开始提供射频能量的一个或多个开关181。另外,在一些实施例中,可基于钳口闭合触发器142的位置来提供射频能量。例如,当完全压下触发器142(表明钳口144被闭合)时,可提供射频能量。另外,根据各种实施例,可在钳口144闭合期间推进刀片175或者可在钳口144闭合以后(例如,在射频能量已施加至组织以后)由临床医生独立地推进刀片175。
图8为图1的外科系统100的图示。在各种实施例中,发生器102可包括若干分离的功能性元件,诸如模块和/或块。不同的功能性元件或模块能够用于驱动不同种类的外科装置104,106。例如,超声发生器模块108可驱动超声装置,诸如超声装置104。电外科/射频发生器模块110可驱动电外科装置106。例如,相应的模块108,110可生成用于驱动外科装置104,106的相应的驱动信号。在各种实施例中,超声发生器模块108和/或电外科/射频发生器模块110可各自与发生器102一体形成。作为另外一种选择,模块108,110中的一个或多个可被提供为电联接到发生器102的单独的电路模块。(模块108和110以虚线显示以示出此部分。)此外,在一些实施例中,电外科/射频发生器模块110可与超声发生器模块108一体形成,或反之亦然。
根据所述实施例,超声发生器模块108可产生特定电压、电流、和频率(例如,55,500周/秒(Hz))的一个或多个驱动信号。所述一个或多个驱动信号可被提供至超声装置104,并且具体地提供至可例如如上所述进行操作的换能器114。在一个实施例中,发生器102能够产生特定电压、电流和/或频率输出信号的驱动信号,所述输出信号可在高分辨率、精度和再现性的情况下阶跃。
根据所述实施例,电外科/射频发生器模块110可生成具有足以使用射频(RF)能执行双极性电外科手术的输出功率的一个或多个驱动信号。在双极性电外科手术应用中。驱动信号可提供至例如电外科装置106的电极177,179,例如,如上文所述。因此,发生器102能够通过将足以处理组织(例如,凝固、烧灼、组织吻合等)的电能施加到组织而达到治疗目的。
发生器102可包括位于例如发生器102控制台的前面板上的输入装置145(图1)。输入装置145可包括生成适于对发生器102的操作进行编程的信号的任何合适的装置。在操作中,用户可使用输入装置145对发生器102的操作进行编程或以其他方式进行控制。输入装置145可包括生成如下信号的任何合适的装置,所述信号可被发生器使用(例如,被容纳在发生器中的一个或多个处理器使用)以控制发生器102的操作(例如,超声发生器模块108和/或电外科/射频发生器模块110的操作)。在各种实施例中,输入装置145包括按钮、开关、指轮、键盘、小键盘、触摸屏监视器、指点装置中的一个或多个,所述输入装置远程连接到通用或专用计算机。在其他实施例中,输入装置145例如可包括合适的用户界面,例如显示于触摸屏监视器上的一个或多个用户界面屏幕。因此,通过输入装置145,用户可设定或程控发生器的各种操作参数,例如,由超声发生器模块108和/或电外科/射频发生器模块110产生的一个或多个驱动信号的电流(I)、电压(V)、频率(f)、和/或周期(T)。
发生器102还可包括位于例如发生器102控制台的前面板上的输出装置147(图1)。输出装置147包括用于为用户提供感观反馈的一个或多个装置。此类装置可包括例如视觉反馈装置(例如,LCD显示屏、LED指示器)、听觉反馈装置(例如,扬声器、蜂鸣器)或触觉反馈装置(例如,触觉致动器)。
尽管发生器102的某些模块和/或块可通过实例进行描述,但是可以理解,更多或更少数量的模块和/或块可被使用,并仍属于实施例的范围内。此外,尽管各种实施例可按照模块和/或块的形式描述以有利于说明,然而此类模块和/或块可通过一个或多个硬件部件和/或软件部件和/或硬件部件与软件部件的组合来实施,所述硬件部件为例如处理器、数字信号处理器(DSP)、可编程逻辑装置(PLD)、专用集成电路(ASIC)、电路、寄存器,所述软件部件为例如程序、子程序、逻辑。
在一个实施例中,超声发生器驱动模块108和电外科/射频驱动模块110可包括被实施成固件、软件、硬件或它们的任何组合的一个或多个嵌入式应用程序。模块108,110可包括各种可执行模块,例如软件、程序、数据、驱动器、应用程序接口(API)等。固件可存储在非易失性存储器(NVM),诸如位屏蔽只读存储器(ROM)或闪速存储器中。在各种具体实施中,将固件存储在ROM中可保护闪速存储器。NVM可包括其他类型的存储器,包括例如可编程ROM(PROM)、可擦可编程ROM(EPROM)、电可擦可编程ROM(EEPROM)或电池支持的随机存取存储器(RAM),诸如动态RAM(DRAM)、双数据率DRAM(DDRAM)和/或同步DRAM(SDRAM)。
在一个实施例中,模块108,110包括实施为处理器的硬件部件,所述处理器用于执行用于监测装置104,106的各种可测量特性的程序指令,并生成用于操作装置104,106的相应一个或多个输出驱动信号。在其中发生器102与装置104结合使用的实施例中,驱动信号可以切割和/或凝固操作模式来驱动超声换能器114。可测量装置104和/或组织的电特性,并且所述电特性可用于控制发生器102的操作方面和/或可作为反馈提供给用户。在其中发生器102与装置106结合使用的实施例中,驱动信号可将电能(例如,射频能量)提供至处于切割、凝固和/或干燥模式的端部执行器132。可测量装置106和/或组织的电特性,并且所述电特性可用于控制发生器102的操作方面和/或可作为反馈提供给用户。在各种实施例中,如先前所讨论的,硬件部件可实施为DSP、PLD、ASIC、电路和/或寄存器。在一个实施例中,处理器能够存储和执行计算机软件程序指令,以生成用于驱动装置104,106的各种部件(诸如超声换能器114和端部执行器126,132)的阶跃函数输出信号。
图9示出根据一个实施例的超声换能器(诸如超声换能器114)的等效电路150。电路150包括第一“动态”支路和第二电容支路,所述第一“动态”支路具有串联连接并限定谐振器的机电性能的电感Ls、电阻Rs和电容Cs,并且第二电容支路具有静态电容C0。可从发生器在驱动电压Vg下接收驱动电流Ig,其中动态电流Im流过第一支路并且电流Ig–Im流过电容支路。可通过适当控制Ig和Vg来实现对超声换能器的机电性能的控制。如上所述,已知的发生器架构可包括调谐电感器Lt(在图9中以虚线显示),该调谐电感器用于使并联谐振电路中谐振频率下的静态电容C0失谐,使得基本上所有发生器电流输出Ig全部流过动态支路。这样,通过控制发生器电流输出Ig来实现对动态支路电流Im的控制。然而,调谐电感器Lt对超声换能器的静态电容C0是特定的,并且具有不同静态电容的不同超声换能器需要不同的调谐电感器Lt。此外,由于调谐电感器Lt与静态电容C0在单一谐振频率下的标称值相匹配,因此仅在该频率下才能确保对动态分支电流Im的精确控制,并且当频率随着换能器温度向下偏移时,对动态支路电流的精确控制会折中。
发生器102的各种实施例可不依赖于调谐电感器Lt来监测动态支路电流Im。相反,发生器102可使用特定超声外科装置104的功率应用中的静态电容C0的测量值(以及驱动信号电压和电流反馈数据)来动态和持续地(例如,实时地)确定动态支路电流Im的值。发生器102的此类实施例因此能够提供虚拟调谐以模拟如下系统,所述系统利用任何频率且非仅为单一谐振频率(通过静态电容C0的标称值指定)下的静态电容C0的任何值来进行调谐或谐振。
图10是发生器102的一个实施例的简化框图,所述发生器如上所述除提供其他有益效果之外还提供无电感器调谐。图11A-11C示出了根据一个实施例的图10的发生器102的架构。参照图10,发生器102可包括患者隔离台152,所述患者隔离台经由功率变压器156与非隔离台154通信。功率变压器156的次线圈158容纳于隔离台152中并且可包括分接头构型(例如,中心分接头或非中心分接头构型)来限定驱动信号输出160a,160b,160c,以用于将驱动信号输出至不同的外科装置,诸如,超声外科装置104和电外科装置106。具体地,驱动信号输出160a,160c可将驱动信号(例如,420VRMS驱动信号)输出至超声外科装置104,并且驱动信号输出160b,160c可将驱动信号(例如,100V RMS驱动信号)输出至电外科装置106,其中输出160b对应于功率变压器156的中心分接头。非隔离台154可包括功率放大器162,所述功率放大器具有连接至功率变压器156的主线圈164的输出。在某些实施例中,功率放大器162可包括例如推挽式放大器。非隔离台154还可包括用于将数字输出提供至数模转换器(DAC)168的可编程逻辑装置166,所述数模转换器(DAC)继而将相应的模拟信号提供至功率放大器162的输入。在某些实施例中,可编程逻辑装置166可包括例如现场可编程门阵列(FPGA)。可编程逻辑装置166通过DAC 168来控制功率放大器162的输入,因此可控制出现在驱动信号输出160a,160b,160c处的驱动信号的多个参数(例如,频率、波形形状、波形振幅)中的任一者。在某些实施例中并且如下所述,可编程逻辑装置166与处理器(例如,下文所述的处理器174)相结合可实施多个基于数字信号处理(DSP)的控制算法和/或其他控制算法以控制通过发生器102输出的驱动信号的参数。
可通过开关模式调节器170将功率提供至功率放大器162的功率导轨。在某些实施例中,开关模式调节器170可包括例如可调式降压调节器。非隔离台154还可包括处理器174,在一个实施例中,所述处理器可包括例如得自MA,Norwood的Analog Devices的DSP处理器,诸如Analog Devices ADSP-21469SHARC DSP。在某些实施例中,处理器174可响应通过处理器174经由模数转换器(ADC)176从功率放大器162接收的电压反馈数据来控制开关模式功率转换器170的操作。在一个实施例中,例如,处理器174可经由ADC 176接收通过功率放大器162放大的信号(例如,RF信号)的波形包迹作为输入。处理器174随后可控制开关模式调节器170(例如,经由脉冲宽度调制(PWM)输出),使得提供至功率放大器162的导轨电压跟踪经放大信号的波形包迹。相对于固定导轨电压放大器方案而言,通过基于波形包迹来动态地调制功率放大器162的导轨电压可显著改善功率放大器162的效率。
在某些实施例中并且如结合图13A-13B更详细所述,可编程逻辑装置166与处理器174相结合可实施直接数字合成器(DDS)控制方案,以控制通过发生器102输出的驱动信号的波形形状、频率和/或振幅。在一个实施例中,例如,可编程逻辑装置166可通过调用存储于动态更新查找表(LUT)(诸如可嵌入在FPGA中的RAM LUT)中的波形样本来实施DDS控制算法268。该控制算法尤其可用于其中超声换能器(诸如超声换能器114)可由其谐振频率下的纯正弦式电流驱动的超声应用。因为其他频率可激发寄生谐振,所以最小化或减小动态支路电流的总失真可相应地最小化或减小不可取的谐振效应。由于发生器102所输出的驱动信号的波形形状受存在于输出驱动电路(例如,功率变压器156、功率放大器162)中的各种失真源的影响,因此可将基于驱动信号的电压和电流反馈数据输入到算法(诸如由处理器174实施的误差控制算法)中,从而通过动态和持续地(例如,实时地)适当预失真或修改存储于LUT中的波形样本来补偿失真。在一个实施例中,施加至LUT样本的预失真的数量或程度可取决于计算的动态支路电流和所需电流波形形状之间的误差,其中所述误差是基于逐个样本确定的。这样,预失真的LUT样本,当通过驱动电路处理时,可产生具有所需波形形状(例如,正弦)的动态支路驱动信号,从而最佳地驱动超声换能器。在此类实施例中,LUT波形样本将因此并不表示驱动信号的所需波形形状,而是表示如下波形形状,其被要求用于最终产生考虑失真效果时的动态支路驱动信号的所需波形形状。
非隔离台154还可包括ADC 178和ADC 180,所述ADC 178和ADC180经由相应的隔离变压器182,184联接到功率变压器156的输出,以分别对由发生器102输出的驱动信号的电压和电流进行采样。在某些实施例中,ADC 178,180能够以高速(例如,80Msps)进行采样,以允许对驱动信号进行过采样。在一个实施例中,例如,ADC 178,180的采样速度可允许驱动信号的大约200x(取决于驱动频率)的过采样。在某些实施例中,可通过单个ADC来执行ADC178,180的采样操作,所述单个ADC经由双路复用器来接收输入电压和电流信号。在发生器102的实施例中使用高速采样可允许(除了别的以外)计算流过动态支路的复合电流(这在某些实施例中可用于实施上述基于DDS的波形形状控制)、精确地数字滤波所采样信号、以及高精度地计算实际功耗。由ADC 178,180输出的电压和电流反馈数据可由可编程逻辑装置166接收和处理(例如,FIFO缓冲、复用)并存储在数据存储器中以用于由例如处理器174的后续检索。如上所述,可将电压和电流反馈数据用作如下算法的输入,所述算法用于动态和持续地预失真或修改LUT波形样本。在某些实施例中,这可能需要每个存储的电压和电流反馈数据对基于相应LUT样本进行索引或以其他方式与相应LUT样本相关联,所述相应LUT样本是当采集电压和电流反馈数据对时由可编程逻辑装置166输出的。以此方式使LUT样本与电压和电流反馈数据同步有助于预失真算法的准确计时和稳定性。
在某些实施例中,可使用电压和电流反馈数据来控制驱动信号的频率和/或幅值(例如,电流幅值)。在一个实施例中,例如,可使用电压和电流反馈数据来确定阻抗相位。然后可控制驱动信号的频率以使所确定的阻抗相位与阻抗相位设定点(例如,0°)之间的差值最小化或减小,由此使谐波失真的影响最小化或减小并相应地增加阻抗相位测量准确性。可在处理器174中实施相位阻抗和频率控制信号的确定,例如,其中将频率控制信号作为输入提供至由可编程逻辑装置166实施的DDS控制算法。
在另一个实施例中,例如,可监测电流反馈数据以保持电流幅值设定点下的驱动信号的电流幅值。可直接指定或者根据指定的电压幅值和功率设定点来间接地确定电流幅值设定点。在某些实施例中,可通过处理器174中的控制算法(例如,比例积分微分(PID)控制算法)来实现电流幅值的控制。通过控制算法控制的可适当控制驱动信号的电流幅值的变量可包括例如存储在可编程逻辑装置166中的LUT波形样本的定标和/或通过DAC 186的DAC 168(其为功率放大器162提供输入)的最大定标输出电压。
非隔离台154还可包括用于提供(除了别的以外)用户接口(UI)功能的处理器190。在一个实施例中,处理器190可包括例如得自California,San Jose的Atmel公司的具有ARM926EJ-S核的Atmel AT91SAM9263处理器。由处理器190支持的UI功能的实例可包括听觉和视觉用户反馈、与外围设备通信(例如,经由通用串行总线(USB)接口)、与脚踏开关120通信、与输入装置112(例如,触摸屏显示器)通信以及与输出装置147(例如,扬声器)通信。处理器190可与处理器174和可编程逻辑装置(例如,经由串行外围接口(SPI)总线)通信。尽管处理器190可主要支持UI功能,但在某些实施例中其也可与处理器174配合来实现减缓风险。例如,处理器190可被程序设计为监测用户输入和/或其他输入(例如,触摸屏输入、脚踏开关120输入、温度传感器输入)的各个方面并可当检测到错误情况时使发生器102的驱动输出无效。
在某些实施例中,处理器174和处理器190两者均可确定和监测发生器102的操作状态。对于处理器174,发生器102的操作状态可指示例如哪些控制和/或诊断方法被处理器174实施。对于处理器190,发生器102的操作状态可指示例如用户接口的哪些元素(例如,显示屏、声音)呈现给用户。处理器174,190可独立地保持发生器102的当前操作状态并且识别和评估当前操作状态中的可能转变。处理器174可充当此关系中的母机并确定何时将发生操作状态之间的转变。处理器190可知道操作状态之间的有效转变并可确定某个特定转变是否适当。例如,当处理器174指示处理器190转变到特定状态时,处理器190可验证所请求转变的有效性。如果状态之间的所请求的转变经处理器190确定为无效,则处理器190可使发生器102进入失效模式。
非隔离台154还可包括用于监测输入装置145的控制器196(例如,电容触摸屏、用于打开和关闭发生器102的电容触摸传感器)。在某些实施例中,控制器196可包括至少一个处理器和/或与处理器190通信的其他控制器装置。在一个实施例中,例如,控制器196可包括处理器(例如,得自Atmel的Mega1688位控制器),所述处理器能够监测经由一个或多个电容触摸传感器提供的用户输入。在一个实施例中,控制器196可包括触摸屏控制器(例如,得自Atmel的QT5480触摸屏控制器)以控制和管理从电容触摸屏对触摸数据的采集。
在某些实施例中,当发生器102处于“功率关”状态时,控制器196可继续接收操作功率(例如,经由来自发生器102的功率源(诸如下述功率源211)的线路)。这样,控制器196可继续监测用于打开和关闭发生器102的输入装置145(例如,位于发生器102的前面板上的电容触摸传感器)。当发生器102处于功率关状态时,如果检测到用户启动“打开/关闭”输入装置145,则控制器196可唤醒功率源(例如,允许操作功率源211的一个或多个DC/DC电压转换器213)。控制器196可因此引发用于将发生器102转变成“功率开”状态的序列。相反地,当发生器102处于功率开状态时,如果检测到启动“打开/关闭”输入装置145,则控制器196可引发用于将发生器102转变成功率关状态的序列。在某些实施例中,例如,控制器196可将“打开/关闭”输入装置145的启动报告给处理器190,所述处理器继而实施用于将发生器102转变成功率关状态的必要处理序列。在此类实施例中,控制器196可不具有用于在发生器102的功率开状态已确立之后从发生器102移除功率的独立能力。
在某些实施例中,控制器196可使发生器102提供听觉或其他感观反馈,以用于提醒用户已引发功率开或功率关序列。可在功率开或功率关序列开始时以及在与该序列相关联的其他过程开始之前提供此类提醒。
在某些实施例中,隔离台152可包括器械接口电路198以例如提供外科装置的控制电路(例如,包括手持件开关的控制电路)和非隔离台154的部件(例如,可编程逻辑装置166、处理器174和/或处理器190)之间的通信接口。器械接口电路198可经由通信连接(例如,基于红外(IR)的通信连接)与非隔离台154的部件交换信息,所述通信连接保持所述台152,154之间适当程度的电隔离。可使用例如低压降稳压器将功率提供至器械接口电路198,所述低压降稳压器通过从非隔离台154驱动的隔离变压器供能。
在一个实施例中,器械接口电路198可包括与信号调节电路202通信的可编程逻辑装置200(例如,FPGA)。信号调节电路202能够从可编程逻辑装置200接收周期信号(例如,2kHz方波),以生成具有相同频率的双极性询问信号。可例如使用由不同差分放大器馈送的双极性电流源来生成询问信号。询问信号可被传送至外科装置控制电路(例如,通过使用将发生器102连接至外科装置的缆线中的导体对)并可被监测以确定控制电路的状态或构型。如下文结合图16-32所讨论,例如,控制电路可包括多个开关、电阻器和/或二极管,以修改询问信号的一个或多个特性(例如,幅值、整流),使得基于所述一个或多个特性可独特地识别控制电路的状态或构型。在一个实施例中,例如,信号调节电路202可包括ADC,所述ADC用于生成出现在控制电路的整个输入的电压信号(因询问信号从中穿过而引起)的样本。可编程逻辑装置200(或非隔离台154的部件)然后可基于ADC样本来确定控制电路的状态或构型。
在一个实施例中,器械接口电路198可包括第一数据电路接口204,以允许可编程逻辑装置200(或器械接口电路198的其他元件)和设置在外科装置中或以其他方式与外科装置相关的第一数据电路之间的信息交换。在某些实施例中并且参照图33E-33G,例如,第一数据电路206可设置在一体地附接到外科装置手持件的缆线中,或者设置在使特定外科装置类型或模型与发生器102交接的适配器中。在某些实施例中,第一数据电路可包括非易失性存储装置,诸如电可擦可编程只读存储器(EEPROM)装置。在某些实施例中并且重新参考图10,第一数据电路接口204可与可编程逻辑装置200独立地实现并包括合适的电路(例如,离散逻辑装置、处理器),以允许可编程逻辑装置200和第一数据电路之间的通信。在其他实施例中,第一数据电路接口204可与可编程逻辑装置200一体形成。
在某些实施例中,第一数据电路206可存储关于与其相关联的特定外科装置的信息。此类信息可包括例如型号、序列号、其中已使用外科装置的多个操作、和/或任何其他类型的信息。该信息可由器械接口电路198(例如,由可编程逻辑装置200)读取、传送至非隔离台154的部件(例如,可编程逻辑装置166、处理器174和/或处理器190)以用于通过输出装置147展示给用户和/或用于控制发生器102的功能或操作。另外,可经由第一数据电路接口204(例如,使用可编程逻辑装置200)将任何类型的信息传送至第一数据电路206以存储于其中。此类信息可包括例如更新的其中已使用外科装置的操作的次数以及/或者其使用的日期和/或时间。
如先前所讨论的,外科器械可从手持件拆卸(例如,器械124可从手持件116拆卸)以提高器械的互换性和/或可处理性。在这种情况下,已知发生器的能力可限于识别所用的特定器械构型和由此优化控制和诊断方法。然而,从兼容性观点来看,将可读数据电路添加至外科装置器械以解决该情况是有问题的。例如,设计与不含必要数据读取功能的发生器保持向后兼容性的外科装置由于例如不同的信号方案、设计复杂性和成本而不切实际。下文结合图16-32所述的器械的实施例通过使用如下数据电路解决了这些问题,所述数据电路可在现有外科器械中以经济且具有最小设计变化的方式实现,从而保持外科装置与当前发生器平台的兼容性。
另外,发生器102的实施例可允许与基于器械的数据电路(诸如,下文结合图16-32和图33A-33C所述的那些)通信。例如,发生器102能够与容纳在外科装置的器械(例如,器械124或134)中的第二数据电路(例如,图16的数据电路284)通信。器械接口电路198可包括第二数据电路接口210以允许该通信。在一个实施例中,第二数据电路接口210可包括三态数字接口,但也可使用其他接口。在某些实施例中,第二数据电路通常可为用于传输和/或接收数据的任何电路。在一个实施例中,例如,第二数据电路可存储关于与其相关联的特定外科装置的信息。此类信息可包括例如型号、序列号、其中已使用外科装置的多个操作、和/或任何其他类型的信息。除此之外或作为另外一种选择,可经由第二数据电路接口210(例如,使用可编程逻辑装置200)将任何类型的信息传送至第二数据电路以存储于其中。此类信息可包括例如其中已使用器械的操作的更新数目以及/或者其使用的日期和/或时间。在某些实施例中,第二数据电路可传输由一个或多个传感器(例如,基于器械的温度传感器)采集的数据。在某些实施例中,第二数据电路可从发生器102接收数据并基于所接收的数据为用户提供指示(例如,LED指示或其他可见指示)。
在某些实施例中,第二数据电路和第二数据电路接口210能够使得可实现可编程逻辑装置200和第二数据电路之间的通信而无需为此目的提供额外的导体(例如,将手持件连接至发生器102的缆线的专用导体)。在一个实施例中,例如,可使用实施于现有缆线(诸如,用于将询问信号从信号调节电路202传输至手持件中的控制电路的导体中的一个)上的单总线通信方案来将信息传送至第二数据电路以及从第二数据电路传送信息。这样,使得可另外必须对外科装置进行的设计变化或修改最小化或减少。此外,如下文结合图16-32和图33A-33C更详细地讨论,由于可在公用物理通道(存在或不存在频带分离)上实现不同类型的通信,第二数据电路的存在可对不具有必要数据读取功能的发生器“不可见”,由此允许外科装置器械的向后兼容性。
在某些实施例中,隔离台152可包括连接至驱动信号输出160b的至少一个阻挡电容器296-1,以阻止DC电流流至患者。单个阻挡电容器可需要遵从例如医疗条例或标准。尽管单个电容器设计的失效为相对不常见的,但此类失效可具有不良后果。在一个实施例中,可提供与阻挡电容器296-1串联的第二阻挡电容器296-2,其中通过例如ADC 298来监测来自阻挡电容器296-1,296-2之间的点的电流泄漏,以用于采样由漏电流引起的电压。可例如通过可编程逻辑装置200接收样本。基于漏电流的变化(如通过图10的实施例中的电压样本指出),发生器102可确定何时阻挡电容器296-1,296-2中的至少一者已失效。因此,图10的实施例与具有单个失效点的单个电容器设计相比可提供有益效果。
在某些实施例中,非隔离台154可包括用于输出合适电压和电流下的DC功率的功率源211。功率源可包括例如用于输出48VDC系统电压的400W功率源。功率源211还可包括一个或多个DC/DC电压转换器213,所述DC/DC电压转换器用于接收功率源的输出,以生成发生器102的各个部件所需的电压和电流下的DC输出。如上文结合控制器196所述,当控制器196检测到用户启动“打开/关闭”输入装置145以允许操作或唤醒DC/DC电压转换器213时,DC/DC电压转换器213中的一个或多个可从控制器196接收输入。
图13A-13B示出了发生器102的一个实施例的某些功能和结构方面。指示从功率变压器156的次线圈158输出的电流和电压的反馈分别通过ADC 178,180接收。如图所示,ADC178,180可实施为2通道ADC并且可以高速(例如,80Msps)采样反馈信号从而允许驱动信号的过采样(例如,大约200x过采样)。在通过ADC 178,180处理之前,可在模拟域中适当调节(例如,放大、滤波)电流和电压反馈信号。在可编程逻辑装置166的块212内,可将来自ADC178,180的电流和电压反馈样本单独缓冲并且随后复用或交叉存取成单个数据流。在图13A-13B的实施例中,可编程逻辑装置166包括FPGA。
可通过在处理器174的块214内实施的并行数据采集端口(PDAP)来接收复用的电流和电压反馈样本。PDAP可包括用于实施使复用反馈样本与存储地址相关联的多种方法中的任一者的包装单元。在一个实施例中,例如,可将与可编程逻辑装置166输出的特定LUT样本相对应的反馈样本存储在一个或多个存储地址处,所述一个或多个存储地址与LUT样本的LUT地址相关联或者是利用LUT样本的LUT地址索引的。在另一个实施例中,可将与可编程逻辑装置166输出的特定LUT样本相对应的反馈样本随同LUT样本的LUT地址一起存储在公用存储位置处。在任何情况下,反馈样本可被存储为使得特定组的反馈样本起源的LUT样本的地址可随后被探知。如上文所述,以此方式使LUT样本地址和反馈样本同步有助于预失真算法的准确计时和稳定性。在处理器174的块216处实施的直接存储存取(DMA)控制器可将反馈样本(以及任何LUT样本地址数据,在适用情况下)存储在处理器174的指定存储位置218(例如,内部RAM)。
处理器174的块220可实施预失真算法,所述预失真算法用于动态、持续地预失真或修改存储在可编程逻辑装置166中的LUT样本。如上所述,LUT样本的预失真可补偿存在于发生器102的输出驱动电路中的各种失真源。预失真的LUT样本,当通过驱动电路进行处理时,将因此产生具有所需波形形状(例如,正弦)的驱动信号,从而最佳地驱动超声换能器。
在预失真算法的块222处,确定通过超声换能器的动态支路的电流。可基于例如存储在存储位置218处的电流和电压反馈样本(其在适当定标时可表示上述图9的模型中的Ig和Vg)、超声换能器静态电容C0的值(测量的或先前已知的)和驱动频率的已知值来使用基尔霍夫(Kirchoff)电流定律确定动态支路电流。可确定与LUT样本相关联的每组存储电流和电压反馈样本的动态支路电流样本。
在预失真算法的块224处,将在块222处确定的每个动态支路电流样本与具有所需电流波形形状的样本进行比较,以确定所比较样本之间的差值或样本幅值误差。为了该确定,可例如从波形形状LUT 226提供具有所需电流波形形状的样本,所述LUT 226包含具有所需电流波形形状的一个周期的幅值样本。来自LUT 226的用于该比较的具有所需电流波形形状的特定样本可通过LUT样本地址指定,所述LUT样本地址与用于该比较的动态支路电流样本相关联。因此,将动态支路电流输入块224可与将其相关联的LUT样本地址同步输入块224。存储在可编程逻辑装置166中的LUT样本与存储在波形形状LUT 226中的LUT样本可因此在数量上相等。在某些实施例中,由存储在波形形状LUT 226中的LUT样本表示的所需电流波形形状可为基本正弦波。其他波形形状可为可取的。例如,应当设想到,可使用用于驱动超声换能器的主纵向运动的基本正弦波,所述超声换能器叠加有一个或多个其他频率下的其他驱动信号,诸如三阶谐波,该三阶谐波用于驱动至少两种机械谐振以用于横向或其他模式的有益振动。
可将在块224处确定的样本幅值误差的每个值连同对其相关联的LUT地址的指示传输至可编程逻辑装置166的LUT(示于图13中的块228处)。基于样本幅值误差的值及其相关联的地址(以及可任选地先前接收的同一LUT地址的样本幅值误差的值),LUT 228(或可编程逻辑装置166的其他控制块)可预失真或修改存储在该LUT地址处的LUT样本的值,使得样本幅值误差减小或最小化。应当理解,在LUT地址的整个范围上以迭代方式对每个LUT样本进行此类预失真或修改将使得发生器的输出电流的波形形状匹配或符合由具有波形形状LUT 226的样本表示的所需电流波形形状。
可在处理器174的块230处基于存储在存储位置218处的电流和电压反馈样本来确定电流和电压幅值测量、功率测量和阻抗测量。在确定这些数量之前,可将反馈样本进行适当定标,并且在某些实施例中通过合适的滤波器232进行处理,以除去由例如数据采集过程和感应谐波分量造成的噪声。经滤波的电压和电流样本因此可基本上表示发生器的驱动输出信号的基频。在某些实施例中,滤波器232可为在频域中应用的有限脉冲响应(FIR)滤波器。此类实施例可使用输出驱动信号电流和电压信号的快速傅里叶变换(FFT)。在某些实施例中,所得的频谱可用于提供附加发生器功能。在一个实施例中,例如,二阶和/或三阶谐波分量相对于基频分量的比率可用作诊断指标。
在块234处,可对表示整数周期的驱动信号的一定样本大小的电流反馈样本应用均方根(RMS)计算,以生成表示驱动信号输出电流的测量Irms。
在块236处,可对表示整数周期的驱动信号的一定样本大小的电压反馈样本应用均方根(RMS)计算,以确定表示驱动信号输出电压的测量Vrms。
在块238处,可将电流和电压反馈样本进行逐点相乘,并且可对表示整数周期的驱动信号的样本进行平均计算,以确定发生器的真实输出功率的测量Pr。
在块240处,可以乘积Vrms·Irms来确定发生器的表观输出功率的测量Pa。
在块242处,可以商Vrms/Irms来确定负载阻抗量值的测量Zm。
在某些实施例中,发生器102可使用在块234、236、238、240和242处确定的数量Irms、Vrms、Pr、Pa和Zm来实施多个控制和/或诊断过程中的任一者。在某些实施例中,可经由例如与发生器102一体形成的输出装置147或者通过合适的通信接口(例如,USB接口)连接至发生器102的输出装置147将这些数量中的任一者传送给用户。各种诊断过程可包括但不限于,例如手持件完整性、器械完整性、器械附接完整性、器械过载、接近器械过载、频锁失效、过电压、过电流、过功率、电压感测失效、电流感测失效、听觉指示失效、视觉指示失效、短路、功率递送失效、阻挡电容器失效。
处理器174的块244可实施相位控制算法以确定和控制通过发生器102驱动的电负载(例如,超声换能器)的阻抗相位。如上所述,通过控制驱动信号的频率以使所确定的阻抗相位和阻抗相位设定点(例如,0°)之间的差值最小化或减小,可使谐波失真的影响最小化或减小,并增加相位测量的准确性。
相位控制算法接收存储在存储位置218中的电流和电压反馈样本作为输入。在将反馈样本用于相位控制算法之前,可将反馈样本进行适当定标,并且在某些实施例中通过合适的滤波器246(其可与滤波器232相同)进行处理,以除去由例如数据采集过程和感应谐波分量造成的噪声。经滤波的电压和电流样本因此可基本上表示发生器的驱动输出信号的基频。
在相位控制算法的块248处,确定通过超声换能器的动态支路的电流。该确定可与上文结合预失真算法的块222所述的确定相同。对于与LUT样本相关联的每组存储电流和电压反馈样本,块248的输出可因此为动态支路电流样本。
在相位控制算法的块250处,基于在块248处确定的动态支路电流样本的同步输入和相应的电压反馈样本来确定阻抗相位。在某些实施例中,该阻抗相位以在波形的上升沿处测量的阻抗相位和在波形的下降沿处测量的阻抗相位的平均值来确定。
在相位控制算法的块252处,将在块222处确定的阻抗相位值与相位设定点254进行比较,以确定所比较值之间的差值或相位误差。
在相位控制算法的块256处,基于在块252处确定的相位误差值和在块242处确定的阻抗量值来确定用于控制驱动信号的频率的频率输出。频率输出值可通过块256进行连续调节并传送至DDS控制块268(下文所述),以便保持在块250处确定的在相位设定点(例如,零相位误差)下的阻抗相位。在某些实施例中,阻抗相位可调节至0°相位设定点。这样,任何谐波失真的中心将位于电压波形的波峰附近,从而增加阻抗相位测量的准确性。
处理器174的块258可实施用于调制驱动信号的电流幅值的算法,以便根据用户指定的设定点或根据由发生器102实施的其他方法或算法指定的要求来控制驱动信号电流、电压和功率。这些数量的控制可通过如下方式实现,例如,通过定标LUT 228中的LUT样本和/或通过经由DAC 186调整DAC 168(其为功率放大器162提供输入)的最大定标输出电压。块260(其在某些实施例中可实施为PID控制器)可从存储位置218接收电流反馈样本(其可进行适当定标和滤波)作为输入。可将电流反馈样本与由受控变量(例如,电流、电压或功率)指定的“电流需求”Id值进行比较,以确定驱动信号是否正提供必需的电流。在其中驱动信号电流为控制变量的实施例中,电流需求Id可由电流设定点262A(Isp)直接指定。例如,可将电流反馈数据(如在块234中确定的)的RMS值与用户指定的RMS电流设定点Isp进行比较,以确定适当的控制器动作。如果例如电流反馈数据指示RMS值小于电流设定点Isp,则可通过块260来调整LUT定标和/或DAC 168的最大定标输出电压,使得驱动信号电流增加。相反地,当电流反馈数据指示RMS值大于电流设定点Isp时,块260可调整LUT定标和/或DAC 168的最大定标输出电压以降低驱动信号电流。
在其中驱动信号电压为控制变量的实施例中,可例如基于在给定负载阻抗量值Zm(在块242处测量)的情况下保持期望电压设定点262B(Vsp)所需的电流来间接地指定电流需求Id(例如,Id=Vsp/Zm)。相似地,在其中驱动信号功率为控制变量的实施例中,可例如基于在给定电压Vrms(在块236处测量)的情况下保持期望功率设定点262C(Psp)所需的电流来间接地指定电流需求Id(例如,Id=Psp/Vrms)。
块268可实施DDS控制算法以用于通过调用存储在LUT 228中的LUT样本来控制驱动信号。在某些实施例中,DDS控制算法可为数控振荡器(NCO)算法,所述数控振荡器(NCO)算法使用点(存储位置)跳过技术来生成固定时钟频率下的波形的样本。NCO算法可实现相位累加器或频率相位转换器(用作从LUT 228调用LUT样本的地址指针)。在一个实施例中,相位累加器可为D步长大小、模N的相位累加器,其中D为表示频率控制值的正整数,并且N为LUT 228中的LUT样本的数量。D=1的频率控制值例如可使相位累加器连续地指向LUT 228的每个地址,从而导致复制存储在LUT 228中的波形的波形输出。当D>1时,相位累加器可跳过LUT 228中的某些地址,从而导致具有较高频率的波形输出。因此,可通过适当地改变频率控制值来控制由DDS控制算法生成的波形的频率。在某些实施例中,可基于在块244处实施的相位控制算法的输出来确定频率控制值。块268的输出可提供DAC168的输入,该输入又将相应的模拟信号提供至功率放大器162的输入。
处理器174的块270可实施开关模式转换器控制算法以基于被放大的信号的波形包迹来动态地调制功率放大器162的导轨电压,从而改善功率放大器162的效率。在某些实施例中,可通过监测包含在功率放大器162中的一个或多个信号来确定波形包迹的特性。在一个实施例中,例如,可通过监测漏电压(例如,MOSFET漏电压)的最小值来确定波形包迹的特性,所述漏电压是根据放大信号的包迹进行调制的。可例如通过联接到漏电压的电压最小值检测器来生成最小电压信号。可通过ADC 176来采样最小电压信号,其中在开关模式转换器控制算法的块272处接收输出最小电压样本。基于最小电压样本的值,块274可通过PWM发生器276来控制PWM信号输出,所述PWM发生器继而通过开关模式调节器170来控制提供至功率放大器162的导轨电压。在某些实施例中,只要最小电压样本的值小于输入到块262中的最低目标278,则可根据如通过最小电压样本表征的波形包迹来调制导轨电压。当最小电压样本指示低包迹功率水平时,例如,块274可使得将低导轨电压提供至功率放大器162,其中仅当最小电压样本指示最大包迹功率水平时才提供满导轨电压。当最小电压样本降至最低目标278之下时,块274可使得导轨电压保持在适于确保功率放大器162的适当操作的最小值。
图33A-33C示出了根据各种实施例的外科装置的控制电路。如上文结合图10所述,控制电路可修改由发生器102传输的询问信号的特性。询问信号的特性(其可独特地指示控制电路的状态或构型)可通过发生器102进行识别并用于控制其操作方面。控制电路可容纳在超声外科装置中(例如,超声外科装置104的手持件116中)或电外科装置中(例如,电外科装置106的手持件130中)。
参见图33A的实施例,控制电路300-1可连接至发生器102以从信号调节电路202(例如,从发生器端子HS和SR(图10)经由缆线112或缆线128的导体对)接收询问信号(例如,2kHz的双极性询问信号)。控制电路300-1可包括第一支路,所述第一支路包括串联连接的二极管Dl和D2以及与D2并联的开关SW1。控制电路300-1还可包括第二支路,所述第二支路包括串联连接的二极管D3、D4和D5、与D4并联的开关SW2、以及与D5并联的电阻器Rl。在某些实施例中并且如图所示,D5可为齐纳二极管。控制电路300-1可另外包括数据存储元件302,所述数据存储元件与第二支路的一个或多个部件(例如,D5、R1)—起定义数据电路304。在某些实施例中,数据存储元件302以及可能地数据电路304的其他部件可容纳在外科装置的器械(例如,器械124、器械134)中,且控制电路300-1的其他部件(例如,SW1、SW2、D1、D2、D3、D4)容纳在手持件(例如,手持件116、手持件130)中。在某些实施例中,数据存储元件302可为单总线装置(例如,单线协议EEPROM)或者其他单线协议或局域互连网络(LIN)协议装置。在一个实施例中,例如,数据存储元件302可包括以商品名“1-Wire”被人所知的得自CA,Sunnyvale的Maxim Integrated Products,Inc.的Maxim DS28EC20EEPROM。数据存储元件302为可容纳在数据电路304中的电路元件的一个实例。数据电路304可除此之外或作为另外一种选择包括能够传输或接收数据的一个或多个其他电路元件或部件。此类电路元件或部件能够例如传输由一个或多个传感器(例如,基于器械的温度传感器)采集的数据和/或从发生器102接收数据并且基于所接收数据为用户提供指示(例如,LED指示或其他可见指示)。
在操作期间,可将来自信号调节电路202的询问信号(例如,2kHz的双极性询问信号)施加至控制电路300-1的整个两个支路上。这样,可通过SW1和SW2的状态独特地确定整个支路上显现的电压。例如,当SW1断开时,用于询问信号的负值的整个控制电路300-1上的电压降将为整个D1和D2上的正向电压降的和。当SW1闭合时,用于询问信号的负值的电压降将仅由D1的正向电压降确定。因此,例如,如果对于D1和D2中的每一者具有0.7伏的正向电压降,则SW1的断开和闭合状态可分别对应于1.4伏和0.7伏的电压降。同样,用于询问信号的正值的整个控制电路300-1上的电压降可由SW2的状态独特地确定。例如,当SW2断开时,整个控制电路300-1上的电压降将为整个D3和D4上的正向电压降(例如,1.4伏)与D5的击穿电压(例如,3.3伏)的和。当SW2闭合时,整个控制电路300-1上的电压降将为整个D3上的正向电压降与D5的击穿电压的和。因此,发生器102可基于显现在控制电路300-1的整个输入上的询问信号电压(例如,如通过信号调节电路202的ADC测量)来识别SW1和SW2的状态或构型。
在某些实施例中,发生器102能够经由第二数据电路接口210(图10)和缆线112或缆线128的导体对来与数据电路304并且具体地与数据存储元件302通信。用于与数据电路304通信的通信协议的频带可高于询问信号的频带。在某些实施例中,例如,用于数据存储元件302的通信协议的频率可为例如200kHz或显著更高的频率,而用于确定SW1和SW2的不同状态的询问信号的频率可为例如2kHz。二极管D5可将提供至数据存储元件302的电压限制于合适的工作范围(例如,3.3-5V)。
如上文结合图10所述,数据电路304并且具体地数据存储元件302可存储关于与其相关联的特定外科器械的信息。此类信息可由发生器102检索并且包括例如型号、序列号、其中已使用外科装置的多个操作、和/或任何其他类型的信息。另外,可将任何类型的信息从发生器102传送至数据电路304以存储于数据存储元件302中。此类信息可包括例如其中已使用器械的操作的更新数目以及/或者其使用的日期和/或时间。
如上所述,数据电路304可除此之外或作为另外一种选择包括除数据存储元件302之外的用于传输或接收数据的部件或元件。此类部件或元件能够例如传输由一个或多个传感器(例如,基于器械的温度传感器)采集的数据和/或从发生器102接收数据并且基于所接收数据为用户提供指示(例如,LED指示或其他可见指示)。
控制电路的实施例可包括额外的开关。参照图33B的实施例,例如,控制电路300-2(共计三个开关)可包括具有第一开关SW1和第二开关SW2的第一支路,其中SW1和SW2状态的每种组合对应于整个控制电路300-2上的唯一电压降以用于询问信号的负值。例如,SW1的断开和闭合状态分别添加或除去D2和D3的正向电压降,并且SW2的断开和闭合状态分别添加或除去D4的正向电压降。在图33C的实施例中,控制电路300-3的第一支路包括三个开关(共计四个开关),其中齐纳二极管D2的击穿电压用于将由操作SW1导致的电压降变化与由操作SW2和SW3导致的电压变化区分开。
图14和15示出了根据各种实施例的外科装置的控制电路。如上文结合图10所述,控制电路可修改由发生器102传输的询问信号的特性。询问信号的特性(其可独特地指示控制电路的状态或构型)可通过发生器102进行识别并用于控制其操作方面。图14的控制电路280可容纳在超声外科装置中(例如,超声外科装置104的手持件116中),并且图15的控制电路282可容纳在电外科装置中(例如,电外科装置106的手持件130中)。
参见图14,控制电路280可连接至发生器102以从信号调节电路202(例如,从发生器端子HS和SR(图10)经由缆线112的导体对)接收询问信号(例如,2kHz的双极性询问信号)。控制电路280可包括与第一二极管D1串联以定义第一支路的第一开关SW1和与第二二极管D2串联以定义第二支路的第二开关SW2。第一支路和第二支路可为并联的,使得D2的正向导电方向与D1的正向导电方向相反。询问信号可施加在整个两个支路上。当SW1和SW2均断开时,控制电路280可定义开路。当SW1闭合并且SW2断开时,询问信号可沿第一方向进行半波整流(例如,询问信号的正半波被阻隔)。当SW1断开并且SW2闭合时,询问信号可沿第二方向进行半波整流(例如,询问信号的负半波被阻隔)。当SW1和SW2均闭合时,可不发生整流。因此,基于对应于SW1和SW2的不同状态的询问信号的不同特性,发生器102可根据显现在控制电路280的整个输入上的电压信号(例如,如通过信号调节电路202的ADC测量)来识别控制电路280的状态或构型。
在某些实施例中并且如图14所示,缆线112可包括数据电路206。数据电路206可包括例如非易失性存储装置,诸如EEPROM装置。发生器102可经由第一数据电路接口204与数据电路206交换信息,如上文结合图10所述。此类信息可特定于与缆线112一体形成的或者能够用于与缆线112一起使用的外科装置,并且可包括例如型号、序列号、其中已使用外科装置的多个操作、和/或任何其他类型的信息。信息也可从发生器102传送至数据电路206以存储于其中,如上文结合图10所述。在某些实施例中并且参照图33E-33G,数据电路206可设置在用于使特定外科装置类型或模型与发生器102交接的适配器中。
参见图15,控制电路282可连接至发生器102以从信号调节电路202(例如,从发生器端子HS和SR(图10)经由缆线128的导体对)接收询问信号(例如,2kHz的双极性询问信号)。控制电路282可包括串联连接的电阻器R2、R3和R4,其中开关SW1和SW2分别跨接在R2和R4上。询问信号可施加到串联连接的电阻器的至少一者上,以在整个控制电路282上生成电压降。例如,当SW1和SW2均断开时,可通过R2、R3和R4来确定电压降。当SW1闭合并且SW2断开时,可通过R3和R4来确定电压降。当SW1断开并且SW2闭合时,可通过R2和R3来确定电压降。当SW1和SW2均闭合时,可通过R3来确定电压降。因此,发生器102可基于整个控制电路282上的电压降(例如,如通过信号调节电路202的ADC测量)来识别控制电路282的状态或构型。
图16示出了超声外科装置(诸如超声外科装置104)的控制电路280-1的一个实施例。除了包括图14的控制电路280的部件之外,控制电路280-1还可包括具有数据存储元件286的数据电路284。在某些实施例中,数据存储元件286以及可能地数据电路284的其他部件可容纳在超声外科装置的器械(例如,器械124)中,其中控制电路280-1的其他部件(例如,SW1、SW2、D1、D2、D3、D4、C1)容纳在手持件(例如,手持件116)中。在某些实施例中,数据存储元件286可为单总线装置(例如,单线协议EEPROM)或者其他单线协议或局域互连网络(LIN)协议装置。在一个实施例中,例如,数据存储元件286可包括以商品名“1-Wire”被人所知的得自CA,Sunnyvale的Maxim Integrated Products,Inc.的Maxim DS28EC20单线EEPROM。
在某些实施例中,发生器102能够经由第二数据电路接口210(图10)和缆线112的导体对来与数据电路284并且具体地与数据存储元件286通信。具体地,用于与数据电路284通信的通信协议的频带可高于询问信号的频带。在某些实施例中,例如,用于数据存储元件286的通信协议的频率可为例如200kHz或显著更高的频率,而用于确定SW1和SW2的不同状态的询问信号的频率可为例如2kHz。因此,数据电路284的电容器C1的值可被选择为使得数据存储元件286对相对低频的询问信号“不可见”,同时允许发生器102在较高频率的通信协议下与数据存储元件286通信。串联的二极管D3可保护数据存储元件286免受询问信号的负向周期,并且并联的齐纳二极管D4可将提供至数据存储元件286的电压限制于合适的工作范围(例如,3.3-5V)。当处于正向导电模式时,D4也可使询问信号的负向周期钳制到地。
如上文结合图10所述,数据电路284并且具体地数据存储元件286可存储关于与其相关联的特定外科器械的信息。此类信息可由发生器102取出并且包括例如型号、序列号、其中已使用外科器械的多个操作、和/或任何其他类型的信息。另外,可将任何类型的信息从发生器102传送至数据电路284以存储于数据存储元件286中。此类信息可包括例如其中已使用器械的操作的更新数目以及/或者其使用的日期和/或时间。此外,由于发生器102和外科装置之间的不同类型的通信可为频带分离的,因此数据存储元件286的存在可对不具有必要数据读取功能的发生器“不可见”,由此允许外科装置的向后兼容性。
在某些实施例中并且如图17所示,数据电路284-1可包括电感器L1,以提供数据存储元件286从SW1和SW2的状态的隔离。添加L1可另外允许在电外科装置中使用数据电路284-1。图18例如示出了将图15的控制电路282与图17的数据电路284-1组合的控制电路282-1的一个实施例。
在某些实施例中,数据电路可包括一个或多个开关,以修改通过数据电路接收的询问信号的一个或多个特性(例如,幅值、整流),使得基于所述一个或多个特性可独特地识别一个或多个开关的状态或构型。图19例如示出了控制电路282-2的一个实施例,其中数据电路284-2包括与D4并联的开关SW3。可从发生器102(例如,从图10的信号调节电路202)以如下频率传送询问信号,所述频率足以使询问信号经由C1被数据电路284-2接收但通过L1与控制电路282-2的其他部分阻隔开。这样,可使用第一询问信号(例如,25kHz下的双极性询问信号)的一个或多个特性来识别SW3的状态,并且可使用较低频率下的第二询问信号(例如,2kHz下的双极性询问信号)的一个或多个特性来识别SW1和SW2的状态。尽管所添加的SW3是结合电外科装置中的控制电路282-2示出的,但是应当理解,SW3可添加至超声外科装置的控制电路,诸如,图17的控制电路280-2。
另外,应当理解,可将除SW3之外的开关添加至数据电路。如图20和21所示,例如,数据电路284-3和284-4的实施例可分别包括第二开关SW4。在图20中,可选择齐纳二极管D5和D6的电压值,使得它们的电压值足够不同,以允许在噪声的存在下可靠地辨别询问信号。D5和D6的电压值的和可等于或小于D4的电压值。在某些实施例中,根据D5和D6的电压值,可以从图20所示的数据电路284-3的实施例中移除D4。
在某些情况下,开关(例如,SW1-SW4)可能阻碍发生器102与数据存储元件286通信的能力。在一个实施例中,如果开关的状态使得其妨碍发生器102与数据存储元件286之间的通信,则通过声明错误来解决该问题。在另一个实施例中,仅当发生器102确定开关的状态将不妨碍通信时,发生器102才可允许与数据存储元件286通信。由于开关的状态在某种程度上可能无法预测,因此发生器102可重复性地进行这种确定。在某些实施例中,添加L1可防止由数据电路外部的开关(例如,SW1和SW2)引起的干扰。对于包含在数据电路内的开关(例如,SW3和SW4),可通过添加电容值显著小于C1的电容器C2(例如,C2<<C1)来实现利用频带分离的开关隔离。包括C2的数据电路284-5、284-6、284-7的实施例分别示于图22-24中。
在图16-24的实施例的任一者中,根据D4的频率响应特性,可能期望或有必要添加与D4并联且指向同一方向的快速二极管。
图25示出了控制电路280-5的一个实施例,其中使用幅值调制的通信协议(例如,幅值调制的单线协议[以商品名“1-Wire”被人所知]、幅值调制的LlN协议)实现发生器102和数据存储元件之间的通信。高频载波(例如,8MHz或更高)上的通信协议的幅值调制显著增加低频询问信号(例如,2kHz的询问信号)和用于图16-24的实施例中的通信协议的本征“基带”频率之间的频带分离。控制电路280-5可类似于图16的控制电路280-1,其中数据电路288包括附加的电容器C3和电阻器R5,所述电容器C3和电阻器R5与D3相结合来解调数据存储元件286所接收的幅度调制的通信协议。如在图16的实施例中,D3可保护数据存储元件286免受询问信号的负向周期,并且D4可将提供至数据存储元件286的电压限制于合适的工作范围(例如,3.3-5V)并且当处于正向导电模式时可将询问信号的负向周期钳制到地。增加的频率分离可允许C1稍小于图16-24的实施例。另外,载波信号的较高频率也可改善与数据存储元件的通信的噪声抗扰度,因为该频率还从可由相同手术室环境中使用的其他外科装置生成的电噪声的频率范围去除。在某些实施例中,载波的相对较高频率与D4的频率响应特性相结合可期望或需要添加与D4并联且指向同一方向的快速二极管。
通过添加电感器L1来阻止由数据电路288外部的开关(例如,SW1和SW2)引起的对数据存储元件286通信的干扰,可将数据电路288用于电外科器械的控制电路中,如图26的数据电路288-1的实施例所示。
除C2和R3以及更可能需要使用的D7之外,图25和26中的实施例类似于图16-24的“基带”实施例。例如,其中可将开关添加至图19-21的数据电路的方式可直接适用于图25和26的实施例(包括从图20的调制载波等效形式中除去D4的可能性)。实施于图22-24中的数据电路的调制载波等效形式可仅需要添加与C2串联的适当大小的电感器L2,以便将附加开关(例如,SW3、SW4)的询问频率与如下中间频带隔离,所述中间频带位于载波频率和数据电路外部的开关的较低询问频率之间。一个此类数据电路282-7的实施例示于图27中。
在图27的实施例中,可解决由SW1和SW2的状态引起的对发生器与数据存储元件286通信的能力的任何干扰,如上文结合图19-24的实施例所述。例如,如果开关状态将阻止通信则发生器102可声明错误,或者仅当发生器102确定开关状态将不引起干扰时,发生器102才可允许通信。
在某些实施例中,数据电路可不包括存储信息的数据存储元件286(例如,EEPROM装置)。图28-32示出了下述控制电路的实施例,所述控制电路使用电阻元件和/或感应元件来修改询问信号的一个或多个特性(例如,幅值、相位),使得可基于所述一个或多个特性来唯一地识别控制电路的状态或构型。
在图28中,例如,数据电路290可包括识别电阻器R1,其中选择C1的值,使得R1对用于确定SW1和SW2的状态的第一低频询问信号(例如,2kHz的询问信号)“不可见”。通过在控制电路280-6的输入处测量来自位于显著较高频带内的第二询问信号的电压和/或电流(例如,幅值、相位),发生器102可利用C1来测量R1的值,以便确定多个识别电阻器中的哪一个容纳在器械中。发生器102可使用此类信息来识别器械或器械的具体特性,使得可最优化控制和诊断方法。可通过如下方式解决由SW1和SW2的状态引起的对发生器测量R1的能力的任何干扰:如果开关状态将阻止测量则声明错误,或者将第二较高频率的询问信号的电压保持在D1和D2的开启电压之下。也可通过如下方式来解决此类干扰:添加与开关电路串联的电感器(图29中的L1)以阻挡第二较高频率的询问信号,同时通过第一、较低频率的询问信号。以此方式添加电感器也可允许使用电外科器械的控制电路中的数据电路290,如图30的数据电路290-2的实施例中所示。
在某些实施例中,可使用允许多个频率下的询问的多个电容器C1来对于给定的信噪比或对于给定组的部件公差而在较多数量的不同R1值之间进行区分。在一个此类实施例中,电感器可设置为与除最低值的C1之外的全部元件串联,以产生用于不同询问频率的特定通带,如图31中的数据电路290-3的实施例所示。
在基于图14的控制电路280的控制电路的实施例中,可在无需频带分离的情况下测量识别电阻器。图32示出了一个此类实施例,其中R1被选择为具有相对较高的值。
图33D-33I示出了可用于在发生器102和外科装置的手持件之间建立电通信的多导体缆线和适配器的实施例。具体地,缆线可将发生器驱动信号传输至外科装置并且允许发生器102和外科装置的控制电路之间的基于控制的通信。在某些实施例中,缆线可与外科装置一体形成或者能够被外科装置的合适连接器可拆除地接合。缆线112-1、112-2和112-3(分别为图33E-33G)可能够用于与超声外科装置(例如,超声外科装置104)一起使用,并且缆线128-1(图33D)可能够用于与电外科装置(例如,电外科装置106)一起使用。缆线中的一个或多个能够与发生器102直接连接,例如缆线112-1。在此类实施例中,缆线可包括数据电路(例如,数据电路206),所述数据电路用于存储关于与其相关联的特定外科装置的信息(例如,型号、序列号、其中已使用外科装置的多个操作、和/或任何其他类型的信息)。在某些实施例中,缆线中的一个或多个可通过适配器连接至发生器102。例如,缆线112-2和112-3可通过第一适配器292(图33I)连接至发生器102,缆线128-1可通过第二适配器294(图33H)连接至发生器102。在此类实施例中,数据电路(例如,数据电路206)可设置在缆线(例如,缆线112-2和112-3)中或适配器(例如,第二适配器294)中。
在各种实施例中,发生器102可与外科装置104,106电隔离,以防止患者体内的不利和可能有害的电流。例如,如果发生器102和外科装置104,106并非为电隔离的,则通过驱动信号提供至装置104,106的电压可潜在地改变由装置104和/或106作用的患者组织的电势,并由此导致患者体内的不利电流。应当理解,当使用不旨在使任何电流通过组织的超声外科装置104时,此类问题可能更为严重。因此,漏电流的有源消除的描述的其余部分是参照超声外科装置104进行描述的。然而,应当理解,本文所述的系统和方法也可适用于电外科装置106。
根据各种实施例,可使用隔离变压器(诸如隔离变压器156)以在发生器102和外科装置104之间提供电隔离。例如,变压器156可提供上述的非隔离台154与隔离台152之间的隔离。隔离台154可与外科装置104通信。驱动信号可通过发生器102(例如,发生器模块108)提供至隔离变压器156的主线圈164并且从隔离变压器的次线圈158提供至外科装置104。然而,考虑到实际变压器的非理想因素,该布置可能不提供完全电隔离。例如,实际变压器可在主线圈和次线圈之间具有杂散电容。杂散电容可妨碍完全电隔离并且允许存在于主线圈上的电势影响次线圈的电势。这可导致患者体内的漏电流。
现代工业标准(诸如国际电工技术委员会(IEC)60601-1标准)将可容许的患者漏电流限制为10μA或更低。可通过在隔离变压器的次线圈和地(例如,大地)之间提供泄漏电容器来无源地减少漏电流。泄漏电容器可用于稳定通过隔离变压器的杂散电容从非隔离侧联接的患者侧电势的变化并由此减少漏电流。然而,当发生器102提供的驱动信号的电压、电流、功率和/或频率增加时,漏电流也可能增加。在各种实施例中,感应的漏电流可增加至超出无源泄漏电容器将其保持在10μA和/或其他漏电流标准之下的能力。
因此,各种实施例均涉及用于有源消除漏电流的系统和方法。图34示出了用于漏电流的有源消除的电路800的一个实施例。可作为发生器102的一部分或结合发生器102来实施电路800。该电路可包括具有主线圈804和次线圈806的隔离变压器802。可在整个主线圈804上提供驱动信号816,由此在整个次线圈806上生成隔离的驱动信号。除了隔离的驱动信号,隔离变压器802的杂散电容808可将驱动信号相对地818的电势的一些分量联接到患者侧上的次线圈806。
泄漏电容器810和有源消除电路812可按如图所示进行提供并且连接在次线圈806和地818之间。有源消除电路812可生成反相驱动信号814,所述反相驱动信号可与驱动信号816具有约180°的相位差。有源消除电路812可电联接到泄漏电容器810,以将泄漏电容器驱动至如下电势,所述电势相对地818与驱动信号816具有约180°的相位差。因此,患者侧次线圈806上的电荷可通过泄漏电容器810而非通过患者而到达地818,由此减少漏电流。根据各种实施例,泄漏电容器810可被设计为满足足够的工业、政府和/或设计标准以用于稳健性。例如,泄漏电容器810可为符合IEC 60384-14标准的Y型电容器和/或可包括多个串联的物理电容器。
图35示出了可通过发生器102实施的用于提供漏电流的有源消除的电路820的一个实施例。电路820可包括发生器电路824和患者侧电路822。发生器电路824可生成和/或调制驱动信号,如本文所述。例如,在一些实施例中,发生器电路824可以类似于上述非隔离台154的方式工作。另外,例如,患者侧电路822可以类似于上述隔离台152的方式工作。
可通过隔离变压器826提供发生器电路824和患者侧电路822之间的电隔离。隔离变压器826的主线圈828可联接到发生器电路824。例如,发生器电路824可在整个主线圈828上生成驱动信号。可根据任何合适的方法在整个主线圈828上生成驱动信号。例如,根据各种实施例,主线圈828可包括可保持为DC电压(例如,48伏)的中心分接头829。发生器电路824可包括分别联接到主线圈828的其他端部的输出级825,827。输出级825,827可使对应于驱动信号的电流流入主线圈828。例如,当输出级827将其输出电压拉至低于中心分接头电压由此使得输出级827从整个主线圈828吸收电流时,可实现驱动信号的正性部分。可在次线圈830中感应相应的电流。同样,当输出级827将其输出电压拉至低于中心分接头电压由此使得输出级825从整个主线圈828吸收相反电流时,可实现驱动信号的负性部分。这可在次线圈830中感应相应的、相反的电流。患者侧电路822可对所分离的驱动信号进行各种信号调节和/或其他处理,所述驱动信号可经由输出线路821,823提供至装置104。
有源消除变压器832可具有主线圈834和次线圈836。主线圈834可电联接到隔离变压器826的主线圈828,使得将驱动信号提供到整个线圈834上。例如,主线圈834可包括两个线圈843,845。第一线圈845的第一端835和第二线圈843的第一端839可电联接到线圈828的中心分接头829。第一线圈845的第二端841可电联接到输出级827,而第二线圈843的第二端837可电联接到输出级825。消除变压器832的次线圈836可联接到地818和消除电容器840的第一电极。消除电容器840的另一个电极可联接到输出线路823。也可在整个次线圈836上并联地电联接任选的负载电阻器838。
根据各种实施例,有源消除变压器的次线圈836可卷绕和/或接线至其他部件840,838,818,使得其极性与主线圈834的极性相反。例如,可在整个次线圈836上感应反相驱动信号。相对于地818,反相驱动信号可与提供于有源消除变压器832的整个主线圈834上的驱动信号具有180°的相位差。与负载电阻器838相结合,次线圈836可在消除电容器840处提供反相驱动信号。因此,因驱动信号而引起出现在患者侧电路822的泄漏电势的电荷可被吸引至消除电容器840。这样,电容器840、次线圈836和负载电阻器838可将潜在漏电流吸收至地818,由此使患者漏电流最小化。
根据各种实施例,可选择部件832,838,840的参数,以使漏电流消除最大化,并且在各种实施例中减少电磁发射。例如,有源消除变压器832可由材料并且根据如下构造制成,所述构造使其匹配隔离变压器826的频率、温度、湿度和其他特性。可选择有源变压器832的其他参数(例如,线匝数、匝数比等),以在使输出感应电流、电磁(EM)发射最小化与因所施加的外部电压产生的漏电流之间实现平衡。例如,电路820能够满足IEC 60601或其他合适的工业或政府标准。可类似地选择负载电阻器838的值。另外,可选择消除电容器840的参数(例如,电容等)以尽可能地匹配产生感应漏电流的杂散电容的特性。
图36示出了可通过发生器102实施的用于提供漏电流的有源消除的电路842的另选实施例。电路842可类似于电路820,然而,有源消除变压器832的次线圈836可电联接到输出线路823。消除电容器823可串联地连接在次线圈836和地818之间。电路842可以类似于电路820的方式工作。根据各种实施例,(例如,当有源消除变压器832为升压变压器时),可使总工作电压(例如,如IEC 60601-1中所定义的)最小化。
图37示出了可通过发生器102实施的用于提供漏电流的有源消除的电路844的另选实施例。电路844可除去有源消除变压器832并将其替换为隔离变压器826的第二次线圈846。第二次线圈846可连接至输出线路823。消除电容器840可串联地连接在第二次线圈846与地之间。第二次线圈可卷绕和/或接线成具有与主线圈828和次线圈830相反的极性。因此,当在整个主线圈828上存在驱动信号时,则如上文所述,可在整个次线圈846上存在反相驱动信号。因此,电路844可以类似于上文参照电路820和842所述的方式来消除漏电流。除去有源消除变压器832(如电路844所示)可降低部件数量、成本和复杂度。
图38示出了可通过发生器102实施的用于提供漏电流的有源消除的电路848的另一个实施例。电路848能够消除因电容联接(如上文所述)以及其他外部效应(例如频率特异性效应(例如,来自功率源的60Hz或其他频率噪声)、路径效应、负载效应等)在患者侧电路822中产生的外部电流。取代电联接到地818,消除电容器840可联接到校正控制电路851,如电路848中所示。电路851可包括数字信号处理器(DSP)850或其他处理器。DSP850可接收输入858(例如,经由模数转换器)。输入858可为往往指示可引起附加漏电流的外部效应的值。此类输入的实例可为例如功率源参数、负载数据(诸如阻抗)、或描述从电路848到装置104的路径的其他值等。基于输入858,DSP 85可获得消除电势,所述消除电势在提供给消除电容器840时可消除因外部效应产生的患者侧电流。消除电势可以数字形式提供给数模转换器852,所述数模转换器可将消除电势的模拟形式提供给消除电容器840。因此,整个消除电容器840上的电压降可取决于整个第二次线圈846上存在的反相驱动信号以及由电路851建立的消除电势。
示出的电路848除去了有源消除变压器832并且具有电路844构型中的电容器840和第二次线圈846。然而,应当理解,校正控制电路851可用于本文所述的构型(例如,820、842、844等)中的任何一者中。例如,可将电路820,842,844中的任何一者的地818替换成校正控制电路851。
图39示出了可通过发生器102实施的用于提供漏电流的消除的电路860的实施例。根据电路860,消除电容器840可连接在隔离变压器826的主线圈828和输出线路823(例如,公用输出线路)之间。这样,反相驱动信号可出现在整个消除电容器840上,由此产生与上述那些类似的漏电流消除效果。
图40示出了可通过发生器102实施的用于提供漏电流的消除的电路862的另一个实施例。电路862可类似于电路860,不同的是消除电容器可连接在输出线路823(例如,公用输出线路)和两个附加电容器864,866之间。电容器864可连接在消除电容器840和隔离变压器826的主线圈828之间。电容器866可连接在消除电容器840和地818之间。电容器864,866的组合可提供到达地的射频(RF)路径,由此可提高发生器102的射频性能(例如,通过减少电磁发射)。
外科发生器(诸如,示意性地示于图10中的发生器102)例如可电联接到多种外科器械。外科器械可包括例如基于射频的器械和基于超声的装置二者。图41示出了根据一个非限制性实施例的插座和连接器接口900。在一个实施例中,接口900包括插座组件902和连接器组件920。连接器组件920可电联接到缆线921的远端,所述缆线最终连接至例如手持式外科器械。图59示出了根据一个非限制性实施例的外科发生器1050。外科发生器1050可包括外科发生器主体1052,所述外科发生器主体通常包括发生器的外壳。外科主体1052可限定用于接收插座组件(诸如,图59中所示的插座组件1058)的孔1054。现在参见图41和59,插座组件902可包括密封件906,以通常阻止流体通过孔1054进入外科发生器1050中。在一个实施例中,密封件906为环氧树脂密封件。
图42为根据一个非限制性实施例的插座组件902的分解侧视图。插座组件902可包括多个部件,诸如磁体212。插座组件902还可包括可排列成大致圆形构造或任何其他合适构造的多个承窝908。图48为根据一个非限制性实施例的承窝908的放大视图。在一个实施例中,承窝908分为两部分并且插座组件902包括九个分为两部分的承窝908,而在其他实施例中可使用更多或更少的承窝。承窝908中的每一个均可限定用于接收导电引脚的内腔910,如下文更详细所述。在一些实施例中,各个承窝908将以不同高度安装在插座组件902内,使得当连接器组件插入到插座组件中时首先接触某些承窝而后接触其他承窝。
图43为根据一个非限制性实施例的连接器组件920的分解侧视图。连接器组件920可包括例如连接器主体922,所述连接器主体包括插入部分924,所述插入部分的尺寸设定成由插座组件902接收,如在下文更详细所述。连接器组件920可包括多个其他部件,例如铁质引脚926、电路板928、和多个导电引脚930。如图54所示,铁质引脚926可为圆柱形的。在其他实施例中,铁质引脚926可为其他形状,诸如矩形。铁质引脚926可为钢、铁、或任何其他被吸引至磁场或者可被磁化的磁性相容材料。铁质引脚926也可具有肩927、或其他类型的侧向延伸特征。现在参见图55,导电引脚930可附连至电路板928并从电路板928延伸。电路板928还可包括装置识别电路,诸如图33E-33G中所示的电路。因此,在各种实施例中,电路板928可带有EEPROM、电阻器、或任何其他电子部件。在一些实施例中,电路板928的部分可进行灌封或以其他方式封装以改善外科装置的无菌性并有助于抗水性。
再次参见图43,连接器组件920还可包括应变消除构件932。如图56所示,应变消除构件932通常接纳缆线负载以防止该负载施加至电路板928和/或承窝908。在一些实施例中,应变消除构件932可包括有助于组装的对准凹口934。再次参见图43,连接器组件920还可包括联接到连接器主体922的防护罩936。图57示出了根据一个非限制性实施例的防护罩936。防护罩936通常可用作相关电缆的弯曲消除件并且可有助于密封连接器组件920。在一些实施例中,防护罩936可扣合到连接器主体922上。对于高压釜应用,防护罩936可为包覆成型部件。在其他实施例中,可使用其他附接技术,诸如粘合剂或旋转焊接。
图44为图41中所示的插座组件902的透视图。图45为插座组件902的分解透视图。图46为插座组件902的前正视图。图47为插座组件902的侧正视图。参见图44-47,插座组件902可包括凸缘950。凸缘950可具有内壁952和外壁954。凸缘表面956跨过内壁952和外壁954。内壁952可包括至少一个弯曲部分和至少一个线性部分。凸缘950的内壁952限定具有独特几何形状的腔体960。在一个实施例中,腔体960由约270度的圆和两个线性部分限定,所述两个线性部分相切于所述圆并且相交以形成角度Θ。在一个实施例中,角度Θ为约90度。在一个实施例中,具有外周边964的中央突起部分962定位在腔体960中。中央突起部分962可具有限定凹陷部968的中央表面966。磁体912(图42)可紧邻凹陷部968定位。如图所示,承窝908可穿过由中央突起部分962的中央表面966限定的孔972而定位。在使用圆形排列的承窝908的实施例中,磁体912可定位在由承窝限定的圆的内部。插座主体904还可限定后凹陷部976(图47)。后凹陷部976的尺寸可被设计为接收密封件906。凸缘表面966可以角度β倾斜(图47)。如图61所示,外科发生器1050的主体1052的表面也可以角度β倾斜。
图49为连接器组件920的透视图,并且图50为连接器组件920的分解透视图。图51为连接器主体922的侧正视图,其中图52和53分别示出连接器主体922的远端和近端的透视图。现在参见图49-53,连接器主体922可具有凸缘980。凸缘980可包括至少一个弯曲部分和至少一个线性部分。
适配器组件1002和1004可包括与连接器主体922(图50)所容纳的部件基本上类似的部件。例如,适配器组件1002和1004可各自容纳具有装置识别电路的电路板。适配器组件1002和1004也可各自容纳铁质引脚和磁体中的一者以有助于与外科发生器的连接。凸缘980的外壁982通常可被成型为类似于插座组件902(图46)的内壁952。凸缘980的内壁984可被成型为类似于中央突起部分962的外周边964。连接器主体922还可具有包括多个孔990的壁988。孔990的尺寸可被设计为接收导电引脚930和铁质引脚926。在一个实施例中,铁质引脚926的肩927的尺寸设定成使得其不能穿过孔990。在一些实施例中,铁质引脚926可能够相对壁988平移。当组装时,铁质引脚926的肩927可定位在壁988和电路板928中间。铁质引脚926可被定位成使得其在连接器组件920插入到插座组件902中时遇到磁体912的磁场。在一些实施例中,当铁质引脚926平移至壁988并且碰撞磁体912时,将通过可听的咔嗒声指示适当的连接。应当理解,各种部件(诸如垫圈)可定位在铁质引脚926和磁体912中间,以减小接合部件的附带的磨损。另外,在一些实施例中,磁体912可联接到连接器组件920并且铁质引脚926可联接到插座组件902。
图58示出了根据各种非限制性实施例的两个适配器组件1002和1004。适配器组件1002和1004允许具有各种几何形状的连接器组件电联接到外科发生器的插座组件。适配器组件1002能够适应具有连接器组件1006的外科器械,并且适配器组件1004能够适应具有连接器组件1008的外科器械。在一个实施例中,连接器组件1006通过缆线1060与基于射频的外科装置相联,并且连接器组件1008通过缆线1062与基于超声的装置相联。应当理解,适配器组件的其他实施例也可适应具有与图58所示的那些不同的连接器组件的外科器械。图59示出了根据一个非限制性实施例的插入到外科发生器1050的插座组件1058中之后的适配器组件1002。图60示出了插入到适配器组件1002中之后并由此电联接到外科发生器1050的连接器组件1006。类似地,图61示出了根据一个非限制性实施例的插入到外科发生器1050的插座组件1058中之后的适配器组件1004。图62示出了插入到适配器组件1004中之后的连接器组件1008。因此,尽管连接器组件1006和1008各自具有不同的几何形状,但两者均可与外科发生器1050一起使用。
参见图58-62,在一个实施例中,适配器组件1002具有包括凸缘1012的远侧部分1010。凸缘1012能够插入到外科器械1050的插座组件1058中并且可类似于例如图52中所示的凸缘980。可将任何数量的导电引脚或其他连接部件定位在远侧部分中以接合插座组件1058。在一个实施例中,适配器组件1002还具有限定腔体1016的近侧部分1014。腔体1016能够接纳特定的连接器组件,诸如连接器组件1006。应当理解,近侧部分1014可基于将与其一起使用的连接器组件的类型进行适当地配置。在一个实施例中,适配器组件1006具有包括凸缘1022的远侧部分1020。凸缘1022能够插入到外科器械1050的插座组件1058中并且可类似于例如图52中所示的凸缘980。适配器组件1004还具有限定腔体1026的近侧部分1024。在例示的实施例中,中央部分1028定位在腔体1026中并能够接纳连接器组件1008。
图63示出了根据一个非限制性实施例的发生器1102的后面板1100的透视图。发生器1102可例如类似于图10所示的发生器102。后面板1100可包括各种输入和/或输出端口1104。后面板1110还可包括电子纸显示装置1106。电子纸显示装置1106可基于电泳,其中将电磁场施加至导电材料,使得导电材料具有移动性。将具有导电性的微粒分布在薄型挠性基底之间,并且微粒(或调色剂粒子)的位置因电磁场的极性的改变而改变,由此显示数据。实现电子纸的技术方法可使用任何合适的技术来实现,诸如液晶、有机电致发光(EL)、反射膜反射型显示、电泳、扭转向列球、或机械反射型显示。一般来讲,电泳为如下现象,其中当粒子悬浮于介质(即,分散介质)中时,粒子为带电荷的,并且当将电场施加至带电粒子时,所述粒子通过分散基质移动到具有相反电荷的电极。与电子纸显示装置有关的其他论述可见于名称为“ELECTRONIC PAPER DISPLAY DEVICE,MANUFACTURING METHOD AND DRIVINGMETHOD THEREOF”的美国专利7,751,115,该专利全文以引用方式并入。
图64示出了图63所示的后面板1110。图65和66提供了后面板1110的放大视图。参见图64-66,电子纸显示装置1106可显示多个信息,诸如序列号、部件号、专利号、报警标记、端口标识符、指示、供应商信息、服务信息、制造商信息、操作信息、或任何其他类型的信息。在一个实施例中,可通过将计算装置连接至发生器1102的通信端口(例如,USB端口)来改变或更新显示在电子纸显示装置1106上的信息。
如图66中所示,在一些实施例中,后面板1100可包括交互部分1108。在一个实施例中,交互部分1108允许用户使用输入装置(诸如按钮1110)将信息输入至发生器1102。交互部分1108还可显示同时显示在发生器1102的前面板(未示出)上的信息。
在使用超声外科装置(诸如超声外科装置104)的外科手术中,端部执行器126将超声能量传输至接触端部执行器126的组织以实现切割和密封动作。以此方式施加超声能量可引起组织的局部加热。可能需要监测和控制此类加热,以使不期望的组织损害最小化和/或优化切割和密封动作的效果。超声加热的直接测量需要端部执行器126中或附近的温度感测装置。尽管基于传感器的超声加热测量在技术上是可行的,但设计复杂性和其他考虑因素可使得直接测量不切实际。发生器102的各种实施例可通过对施加超声能量引起的温度或加热生成估计值来解决该问题。
具体地,发生器102的一个实施例可实施人工神经网络以基于多个输入变量1218来估计超声加热。人工神经网络为基于所经受的已知输入和输出样本来学习输入和输出之间的复杂、非线性关系(该过程通常称为“训练”)的数学模型。人工神经网络可包括连接在一起以执行数据处理任务的简单处理单元或节点的网络。人工神经网络的结构可在一定程度上类似于大脑中的生物神经网络的结构。当为人工神经网络提供输入数据样本时,其产生输出样本。对于特定的处理任务,可通过提供大量的训练数据来训练人工神经网络。这样,人工神经网络可通过改变节点之间的通信“强度”来改变其结构,从而基于训练数据来改善其性能。
图67示出了人工神经网络1200的一个实施例,所述人工神经网络用于生成从使用超声外科装置(诸如超声外科装置104)施加超声能量导致的估计温度Test。在某些实施例中,可在发生器102的处理器174和/或可编程逻辑装置166中实施神经网络。神经网络1200可包括输入层1202、定义隐藏层1206的一个或多个节点1204、和定义输出层1210的一个或多个节点1208。为清楚起见,仅示出一个隐藏层1206。在某些实施例中,神经网络1200可包括一个或多个级联排列的附加隐藏层,其中每个附加隐藏层中的节点1204的数量可等于或不同于隐藏层1206中的节点1204的数量。
层1202,1210中的每个节点1204,1208可包括一个或多个权值w1212、偏差值b1214和转换函数f 1216。在图67中,对这些值和函数使用不同的下标旨在示出这些值和函数中的每一个可不同于其他值和函数。输入层1202包括一个或多个输入变量p 1218,其中隐藏层1206的每个节点1204接收输入变量p 1218中的至少一个作为输入。如图67中所示,例如,每个节点1204可接收全部的输入变量p 1218。在其他实施例中,少于全部的输入变量p 1218可被节点1204接收。将特定节点1204接收的每个输入变量p1218通过相应的权值w1212进行加权,然后加上任何其他以类似方式加权的输入变量p 1218和偏差值b 1214。然后将节点1204的转换函数f 1216应用至所得加和以生成节点的输出。在图67中,例如,节点1204-1的输出可以f1(n1)给出,其中n1=(w1,1·p1+w1,2·p2+···+w1,j·pj)+b1。
输出层1210的特定节点1208可接收来自隐藏层1206的节点1204中的一个或多个的输出(例如,每个节点1208接收来自图67中的相应节点1204-1、1204-2、...、1204-i的输出f1(·)、f2(·)、...、fi(·)),其中将每个接收的输出通过相应权值w 1212进行加权并且随后加上任何其他以类似方式加权的所接收输入和偏差值b 1214。然后将节点1208的转换函数f 1216应用至所得加和以生成节点的输出,该节点的输出对应于神经网络1200的输出(例如,图67的实施例中的所估计温度Test)。尽管图67中的神经网络1200的实施例在输出层1210中包括仅一个节点1208,但在其他实施例中神经网络1200可包括多于一个输出,在这种情况下输出层1210可包括多个节点1208。
在某些实施例中,节点1204,1208的转换函数f 1216可为非线性传递函数。在一个实施例中,例如,转换函数f 1216中的一个或多个可为S形函数。在其他实施例中,转换函数f 1216可包括正切S形函数、双曲正切S形函数、对数S形函数、线性传递函数、饱和线性传递函数、径向基传递函数、或一些其他类型的传递函数。特定节点1204,1208的转换函数f1216可与另一个节点1204,1208的转换函数f 1216相同或不同。
在某些实施例中,通过隐藏层1206的节点1204接收的输入变量p 1218可表示例如已知或据信对因施加超声能量而产生的温度或加热有影响的信号和/或其他数量或状态。此类变量可包括例如以下中的一个或多个:通过发生器102输出的驱动电压、通过发生器102输出的驱动电流、发生器输出102的驱动频率、通过发生器102输出的驱动功率、通过发生器102输出的驱动能量、超声换能器114的阻抗、和施加超声能量的持续时间。另外,输入变量p 1218中的一个或多个可与发生器102的输出无关并且可包括例如端部执行器126的特征(例如,刀片顶端尺寸、几何形状、和/或材料)和超声能量定向的组织的特定类型。
可训练神经网络1200(例如,通过改变或更改权值w 1212、偏差值b1214和转换函数f 1216),使得其输出(例如,图67的实施例中的估计温度Test)适当地近似对于已知值的输入变量p 1218测量的相关性输出。可通过例如以下方式完成训练:提供已知组的输入变量p 1218,将神经网络1200的输入与对应于已知组的输入变量p 1218的测量输出进行比较,并且修改权值w 1212、偏差值b 1214和/或转换函数f 1216,直至神经网络1200的输出和相应测量输出之间的误差低于预先确定的误差水平。例如,可训练神经网络1200直至均方误差低于预先确定的误差阈值。在某些实施例中,可通过神经网络1200来实施训练过程的某些方面(例如,通过网络1200后向传播误差以适应性地调整权值w 1212和/或偏差值b1214)。
图68示出了对于神经网络1200的一个实施例的具体实施而言的在估计温度值Test和测量温度值Tm之间的比较。用于生成图68中的Test的神经网络1200包括六个输入变量p1218:驱动电压、驱动电流、驱动频率、驱动功率、超声换能器的阻抗、和施加超声能量的持续时间。隐藏层1206包括25个节点,并且输出层1210包括单个节点1208。基于对颈动脉血管施加13次超声能量来生成训练数据。在改变输入变量p 1218值的250个样本范围基于IR测量方法来测量实际温度(Tm),其中基于相应的输入变量p 1218的值通过神经网络1200生成估计温度Test。基于从训练数据排除的运行来生成图68所示的数据。在110-190℉的区域内,估计温度Test展示了相当精确地逼近所测量温度Tm。据信,出现在某些区域(诸如,110℉后的区域)中的估计温度Test的不一致性可通过实施特定于这些区域的附加神经网络来最小化或减小。另外,可偏移神经网络1200的经训练输出的数据的不一致性可被识别和程序设计为特殊情况以进一步改善性能。
在某些实施例中,当所估计温度超过用户定义的温度阈值Tth时,发生器102能够控制超声能量的施加,使得所估计温度Test保持为等于或低于温度阈值Tth。例如,在其中驱动电流为神经网络1200的输入变量p 1218的实施例中,驱动电流可作为控制变量进行处理和调节,以使Test与Tth之间的差值最小化或减小。可使用反馈控制算法(例如,PID控制算法)来实施此类实施例,其中Tth输入至控制算法作为设定点,Test输入至算法作为处理变量反馈,并且驱动电流对应于算法的受控输出。在其中驱动电流用作控制变量的情况下,驱动电流值的适当改变应体现在用于训练神经网络1200的输入变量p 1218组中。具体地,如果训练数据反映出恒定驱动电流值,则可降低作为控制变量的驱动电流的有效性,因为神经网络1200可因驱动电流明显对温度不具有影响而减小与其相关联的权值w 1212。应当理解,可使用除驱动电流之外的输入变量p 1218(例如,驱动电压)来使Test和Tth之间的差值最小化或减小。
根据各种实施例,发生器102可根据一个或多个功率曲线来将功率提供至组织切口。功率曲线可定义递送至组织的功率和组织阻抗之间的关系。例如,当组织阻抗在凝固期间改变(例如,增加)时,通过发生器102提供的功率也可根据所应用的功率曲线而改变(例如,降低)。
不同的功率曲线可尤其适用于或不适用于不同类型和/或尺寸的组织切口。强力功率曲线(例如,需要高功率水平的功率曲线)可适用于大组织切口。当将更强力的功率曲线应用至较小的组织切口(诸如,小血管)时,可导致外部灼热。外部灼热可降低外部的凝固/吻合质量并且还可抑制组织内部的完全凝固。类似地,当将较不强力的功率曲线应用至较大组织切口(例如,较大的束)时,可不能实现止血。
图69示出了显示实例功率曲线1306、1308、1310的图表1300的一个实施例。图表1300包括阻抗轴1302,所述阻抗轴示出了从左向右递增的可能组织阻抗。功率轴1304示出了从下向上递增的功率。功率曲线1306、1308、1310中的每一个可定义沿功率轴1304的一组功率水平,所述功率水平对应于沿阻抗轴1302的多个可能感测的组织阻抗。通常,功率曲线可呈现不同的形状,并且这示于图69中。功率曲线1306显示具有阶梯式形状,而功率曲线1308、1310显示具有弯曲形状。应当理解,各种实施例所使用的功率曲线可呈现任何可用的连续或非连续形状。功率曲线的功率递送速率或强度可由其在图表1300上的位置来指示。例如,对于给定组织阻抗递送较高功率的功率曲线可视为较强力的。因此,在两个功率曲线之间,定位在沿功率轴1304的最上方的曲线可为较强力的。应当理解,一些功率曲线可重叠。
可根据任何合适的方法来比较两个功率曲线的强度。例如,如果第一功率曲线在可能组织阻抗的范围的至少一半上具有相应较高的递送功率,则可视为第一功率曲线在给定的可能组织阻抗范围上比第二功率曲线更强力。另外,例如,在给定的可能组织阻抗范围上,如果第一曲线下方在该范围内的面积大于第二曲线下方在该范围内的面积,则可视为第一功率曲线比第二功率曲线更强力。换句话讲,当功率曲线以离散形式进行表示时,如果第一功率曲线在给定组的可能组织阻抗上的功率值的总和大于第二功率曲线在所述组的可能组织阻抗上的功率值的总和,则可视为第一功率曲线在所述组的可能组织阻抗上比第二功率曲线更强力。
根据各种实施例,本文所述的功率曲线移变算法可与任何种类的外科装置(例如,超声装置104、电外科装置106)一起使用。在使用超声装置104的实施例中,可利用电极157,159来获取组织阻抗读数。对于电外科装置,诸如106,可利用第一电极177和第二电极179来获取组织阻抗读数。
在一些实施例中,电外科装置104可包括定位在电极177,179之一或二者与组织切口之间的正温度系数(PTC)材料。PTC材料在其达到阈值或触发温度(在该点,PTC材料的阻抗可增加)之前可具有保持相对较低和相对恒定的阻抗分布。使用时,PTC材料可放置成接触组织,同时施加功率。PTC材料的触发温度可被选择为使得其对应于指示吻合或凝固完成的组织温度。因此,当吻合或凝固过程完成时,PTC材料的阻抗可增加,由此使得实际提供至组织的功率相应地降低。
应当理解,在凝固或吻合过程期间,组织阻抗通常可增加。在一些实施例中,组织阻抗可显示出指示成功凝固的突然阻抗增加。这种增加可由于组织中的生理变化、PTC材料达到其触发阈值等,并且可发生在凝固过程中的任何点处。形成突然阻抗增加可能需要的能量的量可与所作用的组织的热质量有关。任何给定组织切口的热质量可又与切口内组织的类型和数量有关。
各种实施例可利用组织阻抗的这种突然增加来为给定组织切口选择合适的功率曲线。例如,发生器102可选择并且相继地应用较强力的功率曲线,直至组织阻抗达到指示已产生突然增加的阻抗阈值。例如,达到阻抗阈值可指示利用当前应用的功率曲线凝固进展适当。阻抗阈值可为组织阻抗值、组织阻抗的变化速率、和/或阻抗和变化速率的组合。例如,当观察到一定阻抗值和/或变化速率时可达到阻抗阈值。根据各种实施例,不同的功率曲线可具有不同的阻抗阈值,如本文所述。
图70示出了用于将一个或多个功率曲线应用至组织切口的处理流程1330的一个实施例。可使用任何合适数量的功率曲线。可按强度顺序相继地应用功率曲线,直至功率曲线中的一个将组织驱动至阻抗阈值。在1332处,发生器102可应用第一功率曲线。根据各种实施例,第一功率曲线可被选择为以相对低的速率来递送功率。例如,第一功率曲线可被选择为在具有最小和最易受损的预期组织切口的情况下避免组织灼热。
可将第一功率曲线以任何合适的方式应用至组织。例如,发生器102可生成实施第一功率曲线的驱动信号。可通过调制驱动信号的功率来实现功率曲线。可以任何合适的方式来调制驱动信号的功率。例如,可调制信号的电压和/或电流。另外,在各种实施例中,驱动信号可为脉动的。例如,发生器102可通过改变驱动信号的脉冲宽度、占空比等来调制平均功率。驱动信号可提供至电外科装置106的第一电极177和第二电极179。另外,在一些实施例中,可将实施第一功率曲线的驱动信号提供至上述超声装置104的超声发生器114。
当应用第一功率曲线时,发生器102可监测提供至组织的总能量。可在一个或多个能量阈值下将组织阻抗与阻抗阈值进行比较。可存在任何合适数量的能量阈值,所述能量阈值可根据任何合适的方法进行选择。例如,能量阈值可被选择为对应于不同组织类型达到阻抗阈值的已知点。在1334处,发生器102可确定递送至组织的总能量是否已达到或超过第一能量阈值。如果总能量仍未达到第一能量阈值,则发生器102可继续在1332处应用第一功率曲线。
如果总能量已达到第一能量阈值,则发生器102可确定是否已达到阻抗阈值(1336)。如上文所述,阻抗阈值可为预先确定的阻抗变化(例如,增加)速率、预先确定的阻抗、或两者的组合。如果达到阻抗阈值,则发生器102可在1332处继续应用第一功率曲线。例如,在第一功率曲线中达到阻抗阈值可表明第一功率曲线的强度足以形成合适的凝固或吻合。
如果在1336处未达到阻抗阈值,则发生器102可在1338处递增至下一个最强力的功率曲线,并且在1332处将该功率曲线用作当前功率曲线。当在1334处达到下一个能量阈值时,发生器102可再次在1336处确定是否已达到阻抗阈值。如果未达到,发生器102可再次在1338处递增至下一个最强力的功率曲线并且在1332处递送该功率曲线。
处理流程1330可持续进行直至终止。例如,当在1336处达到阻抗阈值时,可终止处理流程1330。在达到阻抗阈值时,发生器102可应用当时电流功率曲线直至完成凝固或吻合。另外,例如,当用尽所有可用功率曲线时,处理流程1330可终止。可使用任何合适数量的功率曲线。如果最强力的功率曲线不能将组织驱动至阻抗阈值,则发生器102可继续应用最强力的功率曲线直至以其他方式(例如,通过临床医生或者在达到最终能量阈值时)终止该过程。
根据各种实施例,处理流程1330可持续进行直至出现终止阈值。终止阈值可指示已完成凝固和/或吻合。例如,终止阈值可取决于组织阻抗、组织温度、组织电容、组织电感、实耗时间等中的一个或多个。可存在单一终止阈值,或者在各种实施例中,不同的功率曲线可具有不同的终止阈值。根据各种实施例,不同的功率曲线可使用不同的阻抗阈值。例如,如果第一功率曲线已不能将组织驱动至第一组织阻抗阈值,则处理流程1330可从第一功率曲线转变为第二功率曲线,并且如果第二功率曲线已不能将组织驱动至第二阻抗阈值,则处理流程1330可随后从第二功率曲线改变为第三功率曲线。
图71示出了显示可结合处理流程1330使用的实例功率曲线1382、1384、1386、1388的图表1380的一个实施例。尽管示出了四条功率曲线1382、1384、1386、1388,但应当理解,可使用任何合适数量的功率曲线。功率曲线1382可表示最不强力的功率曲线并且可首先应用。如果在第一能量阈值下未达到阻抗阈值,则发生器102可提供第二功率曲线1384。可根据需要例如以上述方式使用其他功率曲线1386、1388。
如图71所示,功率曲线1382、1384、1386、1388具有不同的形状。然而,应当理解,通过处理流程1330实施的一组功率曲线中的一些或全部均可具有相同的形状。图72示出了显示可结合图70的处理流程使用的实例同形功率曲线1392、1394、1396、1398的图表的一个实施例。根据各种实施例,同形功率曲线,诸如1392、1394、1396、1398,可为彼此的常数倍。因此,发生器102可通过将不同倍数应用至单个功率曲线来实现同形功率曲线1392、1394、1396、1398。例如,可通过将曲线1392乘以第一常数乘数来实现曲线1394。可通过曲线1392乘以第二常数乘数来生成曲线1396。同样,可通过曲线1392乘以第三常数乘数来生成曲线1398。因此,在各种实施例中,发生器102可通过改变常数乘数而在1338处递增至下一个最强力的功率曲线。
根据各种实施例,可通过发生器102的数字装置(例如,处理器、数字信号处理器、现场可编程门阵列(FPGA)等)来实施处理流程1330。此类数字装置的实例包括例如处理器174、可编程逻辑装置166、处理器190等。图73A-73C示出了如下处理流程,所述处理流程描述可通过发生器102的数字装置执行的用以通常实施上述处理流程1330的例程。图73A示出了用于准备发生器102以作用于新组织切口的例程1340的一个实施例。可在1342处开始新组织切口的启用或启动。在1344处,数字装置可指向第一功率曲线。如上文所述,第一功率曲线可作为处理流程1330的一部分实施的最不强力的功率曲线。指向第一功率曲线可包括指向指示第一功率曲线的确定性公式、指向表示第一功率曲线的查找表、指向第一功率曲线乘数等等。
在1346处,数字装置可重置阻抗阈值标志。如下文所述,设置阻抗阈值标志可指示已达到阻抗阈值。因此,重置标志可指示仍未达到阻抗阈值,如在处理流程1330的开始处可为适当的。在1348处,数字装置可继续进行到下一个例程1350。
图73B示出了可通过数字装置执行的用以监测组织阻抗的例程1350的一个实施例。在1352处,可测量负载或组织阻抗。可根据任何合适的方法和使用任何合适的硬件来测量组织阻抗。例如,根据各种实施例,可使用提供至组织的电流和电压并根据欧姆定律来计算组织阻抗。在1354处,数字装置可计算阻抗变化速率。同样可根据任何合适的方式来计算阻抗变化速率。例如,数字装置可保持组织阻抗的先前值并通过将当前一个或多个组织阻抗值与先前值进行比较来计算变化速率。另外,应当理解,例程1350假定阻抗阈值为变化速率。在阻抗阈值为数值的实施例中,可省去1354。如果组织阻抗的变化速率(或阻抗本身)大于阈值(1356),则可设置阻抗阈值标志。数字装置可在1360处继续进行到下一个例程。
图73C示出了可通过数字装置执行的用于将一个或多个功率曲线提供至组织切口的例程1362的一个实施例。在1364处,可将功率递送至组织,例如,如上文参照图70的1334所述。数字装置可通过以下方式指导功率曲线的递送,例如,通过应用功率曲线以找到每个感测的组织阻抗的相应功率、将相应功率调制到提供至第一电极A20和第二电极A22、换能器114等的驱动信号上。
在1366处,数字装置可计算递送至组织的总累积能量。例如,数字装置可监测功率曲线递送的总时间和在各个时间递送的功率。可从这些值计算出总能量。在1368处,数字装置可确定总能量是否大于或等于下一个能量阈值,例如,这类似于上文参照图70的1334所述的方式。如果未达到下一个能量阈值,则可在1378和1364处继续应用当前功率曲线。
如果在1368处达到下一个能量阈值,则在1370处,数字装置可确定是否设置阻抗阈值标志。阻抗阈值标志的状态可指示是否已达到阻抗阈值。例如,如果已达到阻抗阈值,则可已通过例程1350设置阻抗阈值标志。如果未设置阻抗标志(例如,未达到阻抗阈值),则数字装置可在1372处确定是否仍需实施任何更强力的功率曲线。如果需要,则数字装置可在1374处使例程1362指向下一个、更强力的功率曲线。例程1362可根据1364处的新功率曲线继续(1378)递送功率。如果所有可用的功率曲线均已得到应用,则数字装置可在1376处使针对组织操作的其余部分的累积能量的计算和检查失效。
如果已在1370处设置阻抗标志(例如,已达到阻抗阈值),则数字装置可在1376处使针对组织操作的其余部分的累积能量的计算和检查失效。应当理解,在一些实施例中,累积能量计算可继续进行,而1370、1372、1374、和1376可中断。例如,当累积能量达到预先确定的值时,发生器102和/或数字装置可实现自动关闭。
图74示出了用于将一个或多个功率曲线应用至组织切口的处理流程1400的一个实施例。例如,可通过发生器102(例如,发生器102的数字装置)来实施处理流程1400。在1402处,发生器102可将功率曲线递送至组织。可通过将乘数应用至第一功率曲线来获得功率曲线。在1404处,发生器102可确定是否已达到阻抗阈值。如果仍未达到阻抗阈值,则发生器102可根据总施加能量来增加乘数。这可具有增加所施加功率曲线的强度的作用。应当理解,可周期性或连续地增加乘数。例如,发生器102可以预先确定的周期性间隔来检查阻抗阈值(1404)并增加乘数(1406)。在各种实施例中,发生器102可连续地检查阻抗阈值(1404)并增加乘数(1406)。根据总施加能量来增加乘数可以任何合适的方式来实现。例如,发生器102可应用确定性公式,所述确定性公式接收总接收能量作为输入并且提供相应的乘数值作为输出。另外,例如,发生器102可存储查找表,所述查找表包括总施加能量的可能值和相应乘数值的列表。根据各种实施例,发生器102可将脉动驱动信号提供至组织(例如,通过外科装置104,106中的一者)。根据各种实施例,当达到阻抗阈值时,乘数可保持恒定。发生器102可继续施加功率,例如,直至达到终止阈值。终止阈值可为恒定的,或者可取决于乘数的最终值。
在使用脉动驱动信号的一些实施例中,发生器102可将一个或多个复合负载曲线施加至驱动信号,并最终施加至组织。复合负载曲线,与本文所述的其他功率曲线相似,可随根据测量组织特性(例如,阻抗)来定义将被递送至组织的功率水平。复合负载曲线可另外依据所测量的组织特性来定义脉冲特性,诸如脉冲宽度。
图75示出了描述通过发生器102选择和施加复合负载曲线的框图1450的一个实施例。应当理解,可利用任何合适类型的发生器或外科装置来实施框图1450。根据各种实施例,可使用电外科装置(诸如上文参照图4-7所述的装置106)来实施框图1450。另外,在各种实施例中,可使用超声外科装置(诸如上文参照图2-3所述的外科装置104)来实施框图1450。在一些实施例中,框图1450可与具有切割以及凝固能力的外科装置一起使用。例如,射频外科装置(诸如装置106)可包括用于在凝固之前或期间切断组织的切割刃,诸如刀片175。
重新参见图75,可例如通过发生器102的数字装置来执行算法1452,以选择和应用复合负载曲线1456、1458、1460、1462。算法1452可接收来自时钟1454的时间输入并且还可接收来自传感器1468的回路输入1472。回路输入1472可表示可用于算法1452中以选择和/或施加复合负载曲线的组织性质或特性。此类特性的实例可包括例如电流、电压、温度、反射性、施加至组织的力、谐振频率、谐振频率的变化速率等。传感器1468可为专用传感器(例如,温度计、压力传感器等)或者可为软件实施的传感器,所述软件实施的传感器基于其他系统值来获得组织特性(例如,基于驱动信号来观察和/或计算电压、电流、组织温度等)。算法1452可例如基于回路输入1472和/或来自时钟1454的时间输入来选择复合负载曲线1456、1458、1460、1462中的一者进行应用。尽管示出了四个复合负载曲线,但应当理解,可使用任何合适数量的复合负载曲线。
算法1452可以任何合适的方式应用所选复合负载曲线。例如,算法1452可使用所选复合负载曲线来基于组织阻抗(例如,当前测量的组织阻抗可为回路输入的一部分或可来自回路输入)计算功率水平和一个或多个脉冲特性、或者超声装置104的谐振频率特性。可根据复合负载曲线并基于组织阻抗确定的脉冲特性的实例可包括脉冲宽度、斜坡时间、和休止时间。
在设置点1464处,可将获得的功率和脉冲特性应用至驱动信号。在各种实施例中,可实施反馈回路1474以允许驱动信号的更精确调制。在设置点1464的输出处,可将驱动信号提供至放大器1466,所述放大器可提供合适的放大。可将放大的驱动信号提供至负载1470(例如,通过传感器1468)。负载1470可包括组织、外科装置104,106、和/或电联接发生器102与外科装置104,106的任何缆线(例如,缆线112,128)。
图76示出了处理流程,所述处理流程示出了如通过发生器102(例如,通过发生器102的数字装置)实施的算法1452的一个实施例。可在1476处启动算法1452。应当理解,可以任何合适的方式启动算法1452。例如,可由临床医生在启动外科装置104,106时(例如,通过牵拉或以其他方式致动钳口闭合触发器138,142、开关、手柄等)启动算法1452。
根据各种实施例,算法1452可包括多个区域1478、1480、1482、1484。每个区域可表示组织切口的切割和凝固的不同阶段。例如,在第一区域1478中,发生器102可执行初始组织条件(例如,阻抗)的分析。在第二区域1480中,发生器102可将能量施加至组织以将组织准备用于切割。在第三或切割区域1482中,发生器102可继续施加能量同时外科装置104,106切割组织(例如,对于电外科装置106,可通过推进刀片A18来执行切割)。在第四或完成区域1484中,发生器102可施加切割后能量以完成凝固。
现在参见第一区域1478,发生器102可测量任何合适的组织条件,包括例如电流、电压、温度、反射性、施加至组织的力等。在各种实施例中,可根据任何合适的方式来测量组织的初始阻抗。例如,发生器102可调制驱动信号以向组织提供已知电压或电流。阻抗可源于已知电压和所测量电流,反之亦然。应当理解,作为另外一种选择或除此之外可以任何其他合适的方式来测量组织阻抗。根据算法1452,发生器102可从第一区域1478进行到第二区域1480。在各种实施例中,临床医生可例如通过关闭发生器102和/或外科装置104,106来在第一区域1478中结束算法1452。如果临床医生终止算法1542,则另外可在1486处终止射频(和/或超声)递送。
在第二区域1480中,发生器102可开始通过驱动信号将能量施加至组织,以将组织准备用于切割。可根据复合负载曲线1456、1458、1460、1462来施加能量,如下文所述。根据第二区域1480施加能量可包括根据复合负载曲线1456、1458、1460、1462中的一些或全部将脉冲调制到驱动信号上。在各种实施例中,可按照强度顺序来相继地应用复合负载曲线1456、1458、1460、1462(例如,以适应夹持在器械钳口中的各种类型的组织体积)。
可首先应用第一复合负载曲线1456。发生器102可通过将一个或多个第一复合负载曲线脉冲调制到驱动信号上来应用第一复合负载曲线1456。每个第一复合负载曲线脉冲可具有根据第一复合负载曲线并考虑所测量组织阻抗而确定的功率和脉冲特性。用于第一脉冲的所测量组织阻抗可为在第一区域1478处测量的阻抗。在各种实施例中,发生器102可使用第一复合负载曲线脉冲中的全部或一部分来进行组织阻抗或谐振频率的附加测量。可使用该附加测量来确定后续脉冲的功率和其他脉冲特性。
图77示出了用于生成第一复合负载曲线脉冲的处理流程1488的一个实施例。可通过发生器102(例如,通过发生器102的数字装置)来执行处理流程1488,例如,作为算法1452的一部分。在1490处,发生器102可计算脉冲宽度(Tpw)。可考虑最近的测量组织阻抗(Z)并且根据第一复合负载曲线1456来确定脉冲宽度。
在1492处,发生器102可在斜坡时间(tramp)将驱动信号的功率斜升至高达脉冲功率(PLimit),由此将脉冲施加至组织。可再次考虑最近的测量组织阻抗(Z)并且根据第一复合负载曲线1456来确定脉冲功率。斜坡时间可根据考虑组织阻抗的复合负载曲线来确定或者可为恒定的(例如,对于所有的第一复合负载曲线脉冲为恒定的、对于所有脉冲为恒定的等等)。发生器102可以任何合适的方式(包括例如调制通过驱动信号提供的电流和/或电压)将脉冲功率施加至驱动信号。根据各种实施例,驱动信号可为交流电(A/C)信号,并且因此脉冲本身可包括多个周期的驱动信号。
在1494处,可针对脉冲宽度将驱动信号保持在脉冲功率。在脉冲结束时,在1496处,驱动信号可在下降时间(Tfall)内斜降。下降时间可根据考虑组织阻抗的第一复合负载曲线来确定、或者可为恒定的(例如,对于所有的第一复合负载曲线脉冲而言为恒定的、对于所有脉冲而言为恒定的等等)。应当理解,根据实施例,斜坡时间和下降时间可视为或可不视为脉冲宽度的一部分。在1498处,发生器102可暂停休止时间(Toff)。与斜坡时间和下降时间相似,休止时间可根据考虑组织阻抗的第一复合负载曲线来确定或者可为恒定的(例如,对于所有的第一复合负载曲线脉冲而言为恒定的、对于所有脉冲而言为恒定的等等)。
在休止时间完成时,发生器102可重复处理流程1488,前提条件是应用第一复合负载曲线1456。根据各种实施例,发生器102可将第一复合负载曲线1456应用预先确定的时间量。因此,可重复处理流程1488直至预先确定的时间量已流逝(例如,基于从时钟1454接收的时间输入来确定)。另外,在各种实施例中,可将第一复合负载曲线应用预先确定的脉冲数。由于所应用脉冲宽度根据测量的组织阻抗而改变,因此第一复合负载曲线的应用的总时间也可随测量的组织阻抗而改变。根据各种实施例,第一复合负载曲线1456(以及其他复合负载曲线1458、1460、1462)可规定当组织阻抗增加时降低脉冲宽度。因此,较高的初始组织阻抗可导致在第一复合负载曲线花费较少的时间。
在完成第一复合负载曲线1456之后,发生器102可在第二区域1480的施加中相继地应用其余强化负载曲线1458、1460、1462。可以类似于上述负载曲线1456的方式来应用每个负载曲线1458、1460、1462。例如,可生成根据当前负载曲线的脉冲直至该负载曲线完成(例如,预先确定的时间量或预先确定的脉冲数终了)。对于每个复合负载曲线1456、1458、1460、1462,预先确定的脉冲数可为相同的或者可为不同的。根据各种实施例,可以类似于处理流程1488的方式生成根据负载曲线1458、1460、1462的脉冲,不同的是可根据当前复合负载曲线获得脉冲功率、脉冲宽度以及一些实施例中的斜坡时间、下降时间、和休止时间。
可在发生各种事件时终止第二区域1480。例如,如果总射频施加时间已超过超时时间,则发生器102可在1486处通过终止射频(和/或超声)递送来结束组织操作。另外,各种事件可使得发生器102从第二区域1480转变到第三区域1482。例如,当组织阻抗(Z)超过阈值组织阻抗(Zterm)并且射频能量已递送至少超过最少时间(Tstart)时,发生器102可转变到第三区域1482。阈值组织阻抗可为指示组织切口得以充分准备以便通过刀片175进行切割的阻抗和/或阻抗变化速率。
根据各种实施例,如果在第二区域1480完成之前,最终负载曲线1462在第二区域1480中结束,则可继续应用最终功率曲线1462,例如,直至达到组织阻抗阈值、达到最大第二区域时间和/或达到超时时间。另外,应当理解,对于一些组织切口而言,第二区域1480可在执行所有可用的强化负载曲线1456、1458、1460、1462之前来完成。
在第三区域1482处,发生器102可继续将脉冲调制到驱动信号上。一般来讲,可根据任何合适的方式(包括例如上文参照处理流程1488所述的方式)将第三区域脉冲调制到驱动信号上。可根据任何合适的方法来确定并且在各种实施例中可基于在第二区域1480完成时正执行的复合负载曲线(当前负载曲线)来确定第三区域脉冲的功率和脉冲特性。根据各种实施例,可使用当前负载曲线来确定第三区域脉冲的脉冲功率,而脉冲特性(例如,脉冲宽度、斜坡时间、下降时间、休止时间等)可不管复合负载曲线均为常数。在一些实施例中,第三区域1482可使用特定于第三区域复合负载曲线,所述特定于第三区域复合负载曲线可为用于第二区域1480中的负载曲线1456、1458、1460、1462中的一个、或者可为不同的复合负载曲线(未示出)。
发生器102可继续执行第三区域1482,直至接收到组织切割完成的指示。在使用具有刀片(诸如175)的外科工具的实施例中,当刀片175到达其最远侧位置时(如图6所示),可接收到所述指示。这可使指示刀片175已到达其推进端的刀限位传感器(未示出)跳变。在接收到组织切割完成的指示时,发生器102可继续进行到第四区域1484。还应理解,在一些实施例中,例如如果已达到超时时间,则发生器102可从第三区域1482直接转变到1486处的射频(和/或超声)终止。
在第四区域1484中,发生器102可提供如下能量分布,所述能量分布被设计为完成目前切口组织的凝固。例如,根据各种实施例,发生器102可提供预先确定的脉冲数。可以类似于上文参照处理流程1488所述的方式来提供脉冲。可根据任何合适的方式来确定脉冲的功率和脉冲特性。例如,可基于当前复合负载曲线、特定于第三区域负载曲线、或特定于第四区域复合负载曲线来确定第四区域脉冲的功率和脉冲特性。在一些实施例中,可基于当前复合负载曲线来确定功率,而脉冲特性可特定于第四区域。另外,根据各种实施例,可独立于当前复合负载曲线来确定第四区域脉冲的功率和脉冲特性。
图78示出了脉冲时序图1474的一个实施例,所述脉冲时序图示出了算法1452通过发生器102(例如,通过发生器102的数字装置)的实例应用。第一区域脉冲1502示为位于第一区域1478中。如本文所述,第一区域脉冲1502可用于测量初始组织阻抗。在第一区域脉冲完成时(1509),第二区域1480可开始于所施加的第二区域脉冲1504。可根据各个复合负载曲线1456、1458、1460、1462来施加第二区域脉冲1504,例如,如本文所述。在实例图表1474中,第二区域1480在1510处结束,此时组织达到阈值阻抗(Zterm)。然后如上文所述,利用所施加的第三区域脉冲1506来实施第三区域1482,直至在1512处接收到刀限位信号。在该点,第四区域1484可以施加的第四区域脉冲1508开始,如上文所述,直至在1514处完成循环。
根据各种实施例,发生器102可实现结合算法1452的用户界面。例如,用户界面可指示算法的当前区域。可视觉地和/或听觉地实现用户界面。例如,发生器102可包括用于生成可听音或其他听觉指示的扬声器。至少一个听觉指示可对应于第二区域1480。第三区域1482和第四区域1484也可具有特定于区域的听觉指示。根据各种实施例,第一区域1478也可具有特定于区域的听觉指示。根据各种实施例,听觉指示可包括通过发生器102生成的脉冲音。声音的频率和/或声音的音调本身可指示当前区域。除听觉指示之外或取代听觉指示,发生器102也可提供当前区域的视觉指示(例如,在输出装置147上)。应当理解,临床医生可利用所述用户界面来适当地使用发生器102和相关外科装置104,106。例如,第二区域1480的指示可让临床医生知道组织处理已开始。第三区域1482的指示可让临床医生知道组织已准备用于切割操作。第四区域1484的指示可让临床医生知道切割操作完成。指示和/或最终指示的停止可表明总切割/凝固操作完成。
图79示出了根据实例负载曲线1520的驱动信号电压、电流和功率的图形表示。在图表1520中,驱动信号电压由线1522表示,驱动信号电流由线1524表示,并且驱动信号功率由线1526表示。脉冲宽度未示于图79中。在各种实施例中,由图表1520指示的电压1522、电流1524和功率1526的值可表示单个脉冲内的可能值。因此,可通过添加如下曲线(未示出)将负载曲线1520表示为复合负载曲线,所述曲线指示根据组织阻抗或另一个组织条件的脉冲宽度。如针对负载曲线1520所示,最大电压1522为100伏均方根(RMS)电压,最大电流为3安RMS电流,并且最大功率为135瓦RMS功率。
图79-84示出了多种实例复合负载曲线1530、1532、1534、1536、1538、1540的图形表示。复合负载曲线1530,1532,1534,1536,1538,1540中的每一者可指示基于所测量组织阻抗的脉冲功率和脉冲宽度两者。复合负载曲线1530,1532,1534,1536可单独地或者作为连续较强力复合负载曲线的模式的一部分来进行实施,如上文参照算法1452所述。
图80示出了第一实例复合负载曲线1530的图形表示。复合负载曲线1530可具有45瓦的最大RMS脉冲功率和0.35秒的最大脉冲宽度。在图80中,通过1542指示作为组织阻抗的函数的功率,同时通过1544指示作为组织阻抗的函数的脉冲宽度。下表1示出了针对0Ω至475Ω的组织阻抗的复合负载曲线1530的值。
表1
在各种实施例中,复合负载曲线1530可适用于较小的外科装置和/或较小的组织切口。
图81示出了第二实例复合负载曲线1532的图形表示。复合负载曲线1532可具有45瓦的最大RMS脉冲功率和0.5秒的最大脉冲宽度。在图81中,通过1546指示作为组织阻抗的函数的功率,同时通过1548指示作为组织阻抗的函数的脉冲宽度。下表2示出了针对0Ω至475Ω的组织阻抗的复合负载曲线1532的值。
表2
复合负载曲线1532可作用于小的单个血管组织切口,并且根据各种实施例可为应用于区域二1480中的第一复合功率曲线。
图82示出了第三实例复合负载曲线1534的图形表示。复合负载曲线1534可具有60瓦的最大RMS脉冲功率和2秒的最大脉冲宽度。在图82中,通过1550指示作为组织阻抗的函数的功率,同时通过1552指示作为组织阻抗的函数的脉冲宽度。下表3示出了针对0Ω至475Ω的组织阻抗的复合负载曲线1534的值。
表3
复合负载曲线1534可因其通常较高的功率而比先前曲线1532更强力。复合负载曲线1534与先前曲线1532相比最初可另外具有较高的脉冲宽度,但复合负载曲线1534的脉冲宽度可在仅150Ω处开始下降。根据各种实施例,复合负载曲线1536可用于算法1542中,作为在复合负载曲线1532之后相继实施的负载曲线。
图83示出了第四实例复合负载曲线1536的图形表示。复合负载曲线1536可具有90瓦的最大RMS脉冲功率和2秒的最大脉冲宽度。在图83中,通过1554指示作为组织阻抗的函数的功率,同时通过1556指示作为组织阻抗的函数的脉冲宽度。下表4示出了针对0Ω至475Ω的组织阻抗的复合负载曲线1536的值。
表4
复合负载曲线1536可又比先前曲线1534更强力,并且因此可在算法1452中在曲线1534之后相继地实施。另外,根据各种实施例,复合负载曲线1536可适用于较大的组织束。
图84示出了第五实例复合负载曲线1538的图形表示。复合负载曲线1538可具有135瓦的最大RMS脉冲功率和2秒的最大脉冲宽度。在图84中,通过1558指示作为组织阻抗的函数的功率,同时通过1560指示作为组织阻抗的函数的脉冲宽度。下表5示出了针对0Ω至475Ω的组织阻抗的复合负载曲线1538的值。
表5:
可在算法1452中在先前曲线1536之后相继地使用复合负载曲线1538。
图85示出了第六实例复合负载曲线1540的图形表示。复合负载曲线1540可具有90瓦的最大RMS脉冲功率和2秒的最大脉冲宽度。在图85中,通过1562指示作为组织阻抗的函数的功率,同时通过1564指示作为组织阻抗的函数的脉冲宽度。下表6示出了针对0Ω至475Ω的组织阻抗的复合负载曲线1540的值。
表6:
复合功率曲线1540不如先前功率曲线1538强力。根据各种实施例,可在算法1452中在曲线1538之后相继地实施复合功率曲线1540。另外,在一些实施例中,复合功率曲线1540可在算法1452中实施为特定于第三或第四区域的复合功率曲线。
如上文所述,用于算法1452中的各个复合功率曲线可各自针对预先确定的脉冲数进行实施。下表7示出了针对在算法1452中相继地使用功率曲线1532、1534、1536、1540的示例性实施例各个复合功率曲线的脉冲数。
表7
最后的复合功率曲线1540示出为不具有相应的脉冲数。例如,可实施复合功率曲线1540直至临床医生终止操作、直至达到超时时间、直至达到阈值组织阻抗等。
根据各种实施例,发生器102可以如下方式将功率提供至组织切口,所述方式产生其他组织参数的所需值。图86示出了描述应用算法1572以保持恒定的组织阻抗变化速率的框图1570的一个实施例。可通过发生器102(例如,通过发生器102的数字装置)来实施算法1572。例如,发生器102可利用算法1572来调制驱动信号。传感器1574可感测组织条件,诸如组织阻抗和/或组织阻抗的变化速率。传感器1574可为硬件传感器,或者在各种实施例中可为软件实现的传感器。例如,传感器1574可基于所测量的驱动信号电流和电压来计算组织阻抗。可通过发生器102将驱动信号提供至缆线/工具/负载1576,所述缆线/工具/负载可为组织、外科装置104,106、和将发生器102电联接到装置104,106的缆线112,128的电气组合。
通过实施算法1572,发生器102可监测组织或负载的阻抗,包括例如阻抗的变化速率。发生器102可调制通过驱动信号提供的电压、电流和/或功率中的一者或多者,以保持预先确定的常数值下的组织阻抗变化速率。另外,根据各种实施例,发生器102可将组织阻抗变化速率保持为高于最小的阻抗变化速率。
应当理解,可结合本文所述的各种其他算法来实施算法1572。例如,根据各种实施例,发生器102可将组织阻抗相继地调制为不同的、强度递增的速率,这类似于本文参照本文图70所述的方法1330。例如,可保持第一阻抗变化速率,直至递送至组织的总能量超过预先确定的能量阈值。在能量阈值下,如果组织条件仍未达到预先确定的水平(例如,预先确定的组织阻抗),则发生器102可利用驱动信号将组织驱动至第二、较高的阻抗变化速率。另外,在各种实施例中,可以类似于上文参照复合负载曲线所述的方式来使用组织阻抗变化速率。例如,取代使用多个复合负载曲线,图75的算法1452可能需要应用多个组织阻抗变化速率。可将每个组织阻抗变化速率保持预先确定的时间量和/或预先确定的脉冲数。所述速率可为按照数值顺序而相继施加的(例如,速率可相继地增加)。然而,在一些实施例中,组织阻抗变化的驱动速率可达到峰值并且随后降低。
如上所述,在一个实施例中,发生器102可包括超声发生器模块108,所述超声发生器模块通过以任何合适的方式为换能器114提供驱动信号来驱动超声装置,诸如超声装置104。例如,发生器102可包括脚踏开关120,该脚踏开关经由脚踏开关缆线122联接到发生器102(图8)。可使用控制电路来检测脚踏开关120和超声发生器模块108的存在,使得脚踏开关120的操作对应于超声发生器模块108的启动。因此,临床医生可通过压下脚踏开关120来启动换能器114,并由此启动换能器114和刀片151。在一个实施例中,脚踏开关120可包括多个踏板,其中可启动每个踏板以执行特定功能。在一个实施例中,脚踏开关120可包括例如用于激活和/或控制发生器120的超声模式的第一踏板,以及例如用于激活和/或控制发生器120的电外科模式的第二踏板。因此,发生器102可根据发生器102的有效驱动模式来配置脚踏开关120踏板。
如上所述,发生器102的驱动模式可由装置识别确定。询问信号的特性可独特地指示控制电路的状态或构型,其可通过发生器102进行识别并用于控制其操作方面。先前结合图14-32所述的控制电路280、280-1至280-9、282、以及282-1和282-8中的任何一者能够设置或指示例如发生器102的驱动模式。此类控制电路可容纳在例如超声外科装置中(例如,超声外科装置的手持件中),或者可容纳在电外科装置中(例如,电外科装置的手持件中)。
在一个实施例中,发生器102能够利用超声发生器模块108以超声模式工作。因此,脚踏开关120的第一踏板启用和/或控制超声发生器模块108的工作。在超声模式工作期间,第一踏板(例如,左踏板)能够启动超声发生器模块108的超声输出以生成对应于最小(PMin)超声功率水平(例如,最小能量设置)的驱动信号,并且第二踏板(例如,右踏板)能够启动超声发生器模块108以生成对应于最大(PMax)超声功率水平(例如,最大能量设置)的驱动信号。应当理解,第一踏板或第二踏板能够启动超声发生器模块108以非限制性地生成对应于最小(PMin)或最大(PMax)超声功率水平的驱动信号。因此,可将左踏板或右踏板中的任一者指定为第一踏板,并且可将另一踏板指定为第二踏板。在其中脚踏开关120包括多于两个踏板的实施例中,踏板中的每一个可指定预先确定的功能。在一些实施例中,可通过发生器102的DSP软件或逻辑电路(例如,可执行指令、硬件装置、或它们的组合)来取消或忽略脚踏板中的一者或多者。
在一个实施例中,发生器102被配置成超声模式,并且脚踏开关120包括两个踏板,例如,第一踏板和第二踏板或者左踏板和右踏板。在超声脚踏开关120启动模式期间,当检测到脚踏开关120的第一踏板(例如,左踏板)的有效启动并且超声外科装置104(图8)连接至超声发生器模块108时,发生器102的DSP软件能够以例如最大功率水平来驱动超声外科装置104的超声换能器114。对于超声换能器114而言,可在最大驱动电流(IMax)下获得最大功率(PMax)水平。在其中脚踏开关120包括多于两个踏板的实施例中,可根据上述功能来配置多个踏板中的任意两个。
在一个实施例中,在超声脚踏开关120启动模式期间,当检测到脚踏开关120的第二踏板(例如,右踏板)的有效启动并且超声外科装置104(图8)连接至超声发生器模块108时,发生器102的DSP软件或逻辑器能够以例如最小功率水平来驱动超声外科装置104的超声换能器114。对于超声换能器114,可在最小驱动电流下获得最大功率水平。
在另一个实施例中,发生器102可包括以任何合适方式驱动电外科装置106的电外科/射频发生器模块110。可使用控制电路来检测脚踏开关120和电外科/射频发生器模块110的存在,使得脚踏开关120的操作对应于电外科/射频发生器模块110的启动。因此,发生器102能够利用电外科/射频发生器模块110以电外科模式(例如,双极射频模式)下工作,并且脚踏开关120可包括两个踏板,例如,第一踏板和第二踏板或者左踏板和右踏板。脚踏开关120的第一踏板启用和/或控制电外科/射频发生器模块110的工作。在电外科模式工作期间,第一踏板(例如,左踏板)能够启动电外科/射频发生器模块110的双极射频输出,并且第二踏板(例如,右踏板)开关可被忽略并且可称为停用开关。应当理解,用户可使用停用开关(例如,右踏板)对发生器102进行除功率水平之外的输入。例如,轻踩停用开关踏板可为用户确认或清除故障(除了其他功能以外)、以及用户通过停用开关踏板对发生器进行其他输入的方式。在其中脚踏开关120包括多于两个踏板的实施例中,可根据上述功能来配置多个踏板中的任意两个。
在一个实施例中,在电外科脚踏开关120启动模式期间,当电外科或射频外科装置106(图8)连接至电外科/射频发生器模块110时,发生器102的DSP和用户界面(UI)软件或逻辑器能够忽略脚踏开关120的第二踏板(其为最大启动开关)的状态。因此,当启动脚踏开关120的第二踏板时,不存在功率递送变化并且不存在对用户的视觉或听觉反馈变化。因此,当电外科/射频发生器模块110使得脚踏开关120的第二踏板上的最大开关输入从停用转变成有效而所有其他启动开关输入停用时,电外科/射频发生器模块110忽略来自脚踏开关120的第二踏板的开关输入并且不发声或发出声音。
在一个实施例中,在电外科脚踏开关120启动模式期间,当电外科或射频外科装置106(图8)连接至电外科/射频发生器模块110时,发生器102的DSP软件能够根据特定于电外科或射频装置106预先确定的算法来驱动电外科或射频装置106。各种算法论述于本公开中。
如上所述,根据各种实施例,发生器102可实现结合算法1452(结合图75所述)的用户界面。现在将参照图75和76来描述用户界面的一个实施例,其中图75示出了如下处理流程,该处理流程示出了如通过发生器102(例如,通过发生器102的数字装置)实施的算法1452的一个实施例,并且图76示出了如下处理流程,该处理流程示出了如通过发生器102(例如,通过发生器102的数字装置)实施的算法1452的一个实施例。可在1476处启动算法1452。应当理解,可以任何合适的方式启动算法1452。例如,可由临床医生在启动外科装置104,106时(例如,通过牵拉或以其他方式致动钳口闭合触发器138,142、开关、手柄等)启动算法1452。
因此,在一个实施例中,可实施算法1452以控制如下操作,所述操作为电外科/射频发生器模块110控制电外科或射频外科装置106(图8)。因此,在算法1452的一个实施例中,在电外科或射频外科装置106的启动期间产生第一启动音,当满足阻抗和/或能量条件/阈值时该第一启动音转变成第二启动音,随后当完全满足阻抗和/或能量条件/阈值以及端部执行器132(例如,刀)位置条件时转变成第三启动音。如通过阻抗所确定(如参照结合用于驱动电外科或射频外科装置106的图76所述和所示的算法1452所述),在打开钳口时将声音从第二启动音重置至第三启动音。
因此,现在转到图76,在一个实施例中,算法1452在某些功率递送区域和区域间转变期间控制各种听觉反馈的启动。在一个实施例中,基于发生器102的电外科/射频发生器模块110的操作周期和区域来提供多种听觉反馈。在一个实施例中,例如,当电外科(RF)功率递送周期开始时,发出第一可听音(可听音-I)。例如,每当发生器102的电外科/射频发生器模块110进入第一区域1478并且在第二区域1480中继续时发出第一可听音。
当达到组织阻抗阈值时发出第二可听音(可听音-II)。在一个实施例中,例如,当发生器102的电外科/射频发生器模块110进入第三区域1482时发出第二声音。在一个方面,第二声音可被锁存,使得如果发生从第三区域1482到第二区域1480的转变,则继续发出第二声音。
当电外科(射频)功率递送周期完成时发出第三可听音(可听音-III)。在一个实施例中,当发生器102的DSP软件和/或逻辑器确定已达到“周期完成”状态时,则在第四区域1484中的第四能量脉冲完成时发出第三声音。
仍然参照图76,在一个实施例中,当在组织上行进时,可采用算法1452,其被限定为打开端部执行器132的钳口(图8)(无需释放能量启动)、重新紧抓组织、并且随后继续能量启动。为了适应组织功能的行进,可按如下方式来实施算法1452。当在第二区域1480或第三区域1482中,如果组织阻抗|Zmag|>|Z钳口_打开|,则算法1452重新进入第一区域1478并且实施第一区域1478适用的功率(P)、电流(I)、电压(V)极限。在一个实施例中,当重新进入第一区域1478时,T超时未被重置,并且T开始定时器和能量累积参数被重置。在一个实施例中,当重新进入第一区域1478时,算法1452应引起发出第一可听音(可听音-I),并且再次切换至第二可听音(可听音-II)的逻辑器保持不变,如上文所论述。
应当理解,当发生器102能够利用超声发生器模块108以超声模式工作时,上文所述的声音序列,第一、第二和第三可听音,可用于指示对组织的能量递送。例如,当超声能量递送周期开始时发出第一可听音(可听音-I),当达到组织阻抗阈值时发出第二可听音(可听音-II),并且当超声能量递送周期完成时发出第三可听音(可听音-III)。
图87-99示出提供了外科装置的控制电路的各种额外的实施例。在一个实施例中,控制电路可包括第一电路部分,该第一电路部分联接到能够在打开状态和闭合状态之间进行操作的至少一个开关。第一电路部分通过导体对与外科发生器通信来接收控制信号以确定所述至少一个开关的状态。控制电路还包括联接到至少一个开关的至少一个电阻器,其中可基于所述至少一个电阻器的值确定所述至少一个开关的状态。在一个实施例中,所述至少一个电阻器与所述至少一个开关串联联接。在一个实施例中,所述至少一个电阻器与所述至少一个开关并联联接。在一个实施例中,控制电路包括并联联接到所述至少一个开关的基准电压。在一个实施例中,控制电路包括联接到基准电压的电容器,其中所述至少一个开关的状态可基于电容器上的电压的斜率确定。在一个实施例中,控制电路包括与所述至少一个开关连通的振荡器,其中所述至少一个开关的状态可基于振荡器的频率确定,所述振荡器的频率由所述至少一个电阻器的值确定。在一个实施例中,控制电路包括联接到所述至少一个开关和所述至少一个电阻器的单线多开关输入装置,其中所述至少一个开关的状态可基于所述至少一个电阻器确定并通过单线通信协议被传送至发生器。在一个实施例中,控制信号为具有正相位和负相位的差分恒定电流脉冲。在一个实施例中,控制电路包括第二电路部分,该第二电路部分包括联接到第一电路部分的数据电路元件。在一个实施例中,数据电路元件包括至少一个存储器装置。在一个实施例中,该至少一个存储器装置包括至少一个单线电可擦可编程只读存储器(EEPROM)。
在各种实施例中,提供了外科装置的控制电路。在一个实施例中,控制电路包括第一电路部分,该第一电路部分联接到能够在打开状态和闭合状态之间进行操作的至少一个开关。第一电路部分通过导体对与外科发生器通信来接收来自输入端子的控制信号以确定所述至少一个开关的状态。控制信号具有第一相位和第二相位。第一晶体管联接在输入端子和第一电容器之间,并且第一电阻器与第一电容器串联地联接。在控制信号的第一相位期间,当第一电容器充电至预先确定的电压时,第一晶体管保持在截止模式,并且在控制信号第二相位的初始部分期间,第一晶体管从截止模式转变至饱和模式并保持在饱和模式,直至第一电容器通过第一电阻器放电。在控制信号第二相位的最后部分期间,当第一电容器电压降至预先确定的阈值以下时,第一晶体管从饱和模式转变至截止模式。在一个实施例中,在控制信号第二相位的初始部分期间,当第一晶体管处于饱和模式时,第一阻抗呈现在输入端子之间,并且在控制信号第二相位的最后部分期间,当第一晶体管处于截止模式时,第二阻抗呈现在输入端子之间,其中所述至少一个开关的状态可基于第一阻抗值和第二阻抗值确定。在一个实施例中,控制电路包括联接到所述至少一个开关的至少一个第二电阻器,其中当所述至少一个开关处于打开状态时,第二阻抗至少部分地基于所述至少一个第二电阻器。在一个实施例中,控制电路包括联接到所述至少一个开关的至少一个第二电阻器,其中当所述至少一个开关处于闭合状态时,第二阻抗至少部分地基于所述至少一个第二电阻器。在一个实施例中,控制电路包括第二晶体管,所述第二晶体管联接到第一电容器,以在控制信号的第一相位期间对第一电容器进行充电。在一个实施例中,控制电路包括第二电路部分,该第二电路部分包括联接到第一电路部分的数据电路元件,其中第一电容器电压足以向数据元件提供电压。在一个实施例中,控制电路包括并联联接到所述至少一个开关的基准电压。在一个实施例中,控制电路包括联接到基准电压的第二电容器,其中所述至少一个开关的状态可基于第二电容器上的电压的斜率确定。在一个实施例中,控制信号的第一相位为电流脉冲的正转变,并且控制信号的第二相位为电流脉冲的负转变。
在各种实施例中,提供了一种方法。在一个实施例中,该方法包括在外科装置的控制电路处接收控制信号,并基于电阻器的值确定至少一个开关的状态。控制电路包括联接到能够在打开状态和闭合状态之间进行操作的至少一个开关的第一电路部分,所述第一电路部分通过导体对与外科发生器通信来接收控制信号,所述第一电路部分包括联接到所述至少一个开关的至少一个电阻器。在一个实施例中,该方法包括基于所述至少一个开关的状态在控制信号的第一相位期间呈现第一阻抗并在控制信号的第二相位期间呈现第二阻抗,其中确定所述至少一个开关的状态包括将第一阻抗与第二阻抗进行比较。在一个实施例中,该方法包括在控制信号的第一相位期间生成第一电压斜率,并且在控制信号的第二相位期间生成第二电压斜率,其中确定所述至少一个开关的状态包括将第一电压斜率与第二电压斜率进行比较。在一个实施例中,该方法包括在控制信号的第一相位期间生成第一频率并且在控制信号的第二相位期间生成第二频率,其中确定所述至少一个开关的状态包括将第一频率与第二频率进行比较。在一个实施例中,该方法包括通过联接到所述至少一个开关的单线多开关输入装置读取所述至少一个电阻器的值并通过单线通信协议将所述至少一个电阻器的值传送至发生器。
结合图87-99所公开的控制电路适于与外科装置一起使用,所述外科装置包括例如一次性外科装置。控制电路可克服诸如成本约束、非理想的外科装置使用条件以及与现有设备的兼容性方面的挑战。
此外,由于清洁剂在外科装置手持件触点上形成了残余物,因此开关线路中的串联电阻可随时间推移和使用而增大。结合图87-99描述的控制电路中的每一个的构型和检测方法能够与以下要求的任何一个、任何组合或其全部一起进行操作:与恒定电流源具备兼容性,所述恒定电流源使用如可在发生器102中提供的电压水平状态检测;为针对缆线112(例如,线路)阻抗(即,受污染的手持件触点)的补偿电路;支持针对设置在外科装置手持件上的多个开关的功能(具有可伸缩设计以支持外科装置手持件上的一个、两个、三个或更多个开关);提供电路存在状态;支持针对多个同步开关状态的功能;支持针对多个单线存储器部件的功能(功率和通信);一次性装置具有低成本;最大程度地使用“现成的”部件;使电路占有面积最小化(例如,大约15mm×15mm);提供对由于单点部件失效所导致的危害性状况(例如,开路/短路)的缓解;提供静电放电(ESD)缓解。
结合图87-99所述的控制电路的各种实施例能够位于外科器械的手持件中。控制电路接收由发生器102通过缆线112所传输的询问信号。如上文结合图10所述,控制电路可修改由发生器102传输的询问信号的特性。询问信号的特性(其可独特地指示外科装置的控制电路和/或手持件的状态或构型)可通过位于发生器102侧面处的电路进行识别并用于控制其操作方面。结合图87-99所述的控制电路的各种实施例可容纳在超声外科装置中(例如,超声外科装置104的手持件116中)、电外科装置中(例如,电外科装置106的手持件130中)、或组合型超声/电外科装置中(例如,在单个手持件中结合了超声装置104和电外科装置106的功能性方面的装置的手持件中),如本文所述。
图87示出控制电路1602的一个实施例,所述控制电路包括具有高速数据通信支持的并行切换电阻电路和包括至少一个存储器装置的至少一个数据元件。在一个实施例中,控制电路1602可被差分电流脉冲形式的控制信号操作。如图87所示,在一个实施例中,控制电路1602可经由缆线112(和/或缆线128)连接或联接到发生器102以从信号调节电路202(例如,从图10所示的发生器端子HS和SR经由缆线112或缆线128的导体对)接收询问信号(例如,预先确定的频率(诸如2kHz)的双极性询问信号)。在一个实施例中,控制电路1602包括多个并联开关SW1,SW2,SWn。图87中的控制电路1602的实施例可采用与固定电阻器R1并联的任何合适数量n的开关。因此,任何合适数量的开关SWn(其中n为大于零的整数)可与预先确定的固定电阻并联定位,以提供对外科装置1600(例如,超声装置104、电外科装置106、或组合的超声装置104/电外科装置106)的构型和/或操作的指示。开关的数量n决定可能状态的数量。例如,单个开关SW1可指示最多两种状态,两个开关可指示最多四种状态,并且n个开关可指示最多2n种状态。开关SW1,SW2,SWn可为任何类型的开关。在一个实施例中,开关SW1,SW2,SWn为位于外科装置1600的手持件上的按钮开关。然而,所述实施例不限于该上下文。
根据例如开关SW1,SW2,SWn中每一者的断开或闭合状态,信号调节电路202(例如,从图10所示的发生器端子HS和SR经由缆线112,128的导体对)将获悉不同的阻抗(例如,电阻)。对于例如其中n=2,即采用两个开关SW1,SW2的实施例,信号条件调节电路202可检测到四个独特开关可配置阻抗,如下表8中所述:
询问信号可联接在控制电路1602的输入HS/SR两端,并且施加在开关SW1,SW2的整个两个支路上。当SW1和SW2均断开时,控制电路280可定义对应于第一状态的开路。当SW1断开并且SW2闭合时,询问信号可定义第二状态。当SW1闭合并且SW2断开时,询问信号可定义第三状态。当SW1和SW2均闭合时,询问信号可定义第四状态。因此,基于对应于SW1和SW2的不同状态的询问信号的不同特性,发生器102可根据显现在控制电路280的整个输入上的电压信号(例如,如通过信号调节电路202的ADC测量)来识别控制电路280的状态或构型。
仍然参见图87,在一个实施例中,控制电路1602包括横跨控制电路1602的HS/RS端子放置的二极管D1,以钳制和保护控制电路1602以使其在外科装置1600连接至发生器102和从发生器102断开时不会出现来自外科装置1600和发生器102的静电放电(ESD)和/或瞬变。在例示的实施例中,二极管D1为双向瞬态电压抑制器。可基于预先确定的ESD额定功率(诸如8kV触点放电、5V标称工作电压)、小尺寸、以及将对脉冲波形的影响降至最小的低电容选择二极管D1。可非限制性地采用任何合适的双向瞬态电压抑制器。在其他实施例中,如图93-95和图97所示,例如,多个二极管可横跨输入HS/SR放置,以保护外科装置1600和/或控制电路1602免受ESD和其他瞬变。
提供二极管D2以将负电流脉冲单向路由至通过开关SW1,SW2,SWn配置的电阻器网络R1,R2,R3和Rn+1。在例示的实施例中,二极管D2为单个肖特基二极管,以提供低电压降并最小化对发生器102的ADC的可用电压范围的影响。二极管D2可以离散的形式,作为多二极管包装件的一部分提供,或可形成为定制集成电路(例如,以及ASIC)的一部分。在其他实施例中,可非限制性地采用其他合适的二极管。在电流脉冲的正相位(上升沿)期间,二极管D2反向偏压,并且电流流过晶体管M1,该晶体管M1通过二极管D3对栅极电容器C2充电。在电流脉冲的负相位(下降沿)期间,二极管D2正向偏压并且发生器102的ADC获悉由开关SW1,SW2,SWn配置的电阻器网络R1,R2,R3和Rn+1的阻抗。在其他实施例中,可如结合图92-95和图97所示采用一对二极管以提供双向功率。
提供晶体管M1以将来自发生器102的正电流脉冲路由至栅极电容器C2。在例示的实施例中,虽然晶体管M1为p-通道MOSFET,但在其他实施例中,可非限制性地使用任何合适的晶体管。在例示的实施例中,晶体管M1的漏极端子连接至HS输入端子和二极管D1,D2的阴极,并且栅极端子连接至外科装置1600的SR输入端子。晶体管M1的源极通过电阻器R5连接至SR输入端子。在HS端子处接收的正电流脉冲(如参照图88更详细地描述)通过M1对电容器C2充电。电容器C2联接到晶体管M2的栅极,并且在充电时其可在电流脉冲的负相位期间导通晶体管M2或在输入电流脉冲的正相位期间将功率提供至至少一个存储器装置1604。虽然晶体管M1显示为分立部件,但是其可提供为多晶体管包装件,或可形成为定制集成电路(例如,以及ASIC)的一部分。在其他实施例中,可非限制性地采用其他合适的晶体管。
在一个实施例中,至少一个存储器装置1604可包括例如以商品名“1-Wire”为人所知的一个或多个单线EEPROM。如之前所述,单线EEPROM为单线存储器装置1604。一般来讲,可在控制电路1602中使用多个EEPROM。在例示的实施例中,可在外科装置1600中使用最多两个EEPROM。在电流脉冲的正相位期间为EEPROM供电。晶体管M1还提供低正向电压降并将对EEPROM高速通信的影响降至最低。晶体管M1提供反向阻隔能力,该能力是使用简单的二极管不能实现的。
为了使ADC进行初始基准测量,第二晶体管M2提供显著低阻抗路径以使电阻器网络R1,R2,R3,Rn+1短路。晶体管M2的漏极端子连接至二极管D2的阳极以及电阻器R1,R2,R3和Rn+1的一端。晶体管M2的源端子连接至外科装置1600的SR端子。在示例性实施例中,虽然晶体管M2也是p-通道MOSFET晶体管,但在其他实施例中,可以使用任何合适的晶体管。在电流脉冲的正相位期间,晶体管M2导通并且横跨外科装置1600的HS/RS端子施加显著低阻抗路径相对短的持续时间,该相对短的持续时间如通过晶体管M2的栅极端子上的RC时间常数所定义,其中RC时间常数由电阻器R4和栅极电容器C2确定,所述电阻器R4和栅极电容器C2中的每一者均联接到晶体管M2的栅极。电阻器R4为栅极电容器C2的电压衰减提供放电路径和计时。当晶体管M2截止或开路时,栅极电容器C2在电流脉冲的正相位期间充电。最后,栅极电容器C2上的电压足以将门源极负向偏压,并在电流脉冲的负相位期间将晶体管M2导通。然后通过发生器102中的信号调节电路202的ADC获得第一测量,所述第一测量在本文中是指例如如图90所示的“ADC_NEG1”测量。
二极管D3在电流脉冲的正相位期间提供电流路径,并使栅极电容器C2能够在绕开电阻器R4时快速充电,所述电阻器R4为栅极电容器C2提供放电路径。在一个实施例中,可由于明确定义的最小栅极阈值和最大栅极阈值对晶体管M2进行选择,从而提供对差分测量的导通/截止(ON/OFF)计时的较好表征。在一个实施例中,晶体管M2部件可提供为独立式分立部件,或在同一个包装件中作为晶体管M1提供。可基于1%容限、100ppm温度系数和小包装件尺寸来选择电阻器R4。所识别的部件选择标准仅作为非限制性实例提供。可替换任何合适的部件以执行所需的功能。
如先前所述,电阻器网络R1,R2,R3和Rn+1通过开关SW1,SW2,SWn进行配置,以将不同的电阻(例如,阻抗)提供至发生器102的ADC。例如当所有开关SW1,SW2,SWn均断开(“切断”)时,电阻器R1设置用于开关检测的最大电阻。例如,当SW1闭合(“接通”)时,电阻器R2与其他开关检测电阻器并联定位,如表8所示。例如,当SW2闭合(“接通”)时,电阻器R3与其他开关检测电阻器并联定位,如表8所示。可基于1%容限、100ppm温度系数和小包装件尺寸来非限制地选择电阻器R1,R2,R3,Rn+1中的每一者。电容器C1可与电阻器R1,R2,R3和Rn+1并联定位,以提供例如从传导和/或辐射噪声的高频滤波。在一个实施例中,电容器C1可为陶瓷电容器,但并不排除其他电容器类型。
电阻器R5在电流脉冲的负相位起始期间提供相对低阻抗路径以快速导通晶体管M2。栅极电容器C2结合电阻器R4充电,以在短时间内增大栅极电压超过晶体管M2的导通阈值。也可选择电阻器R5的值以在电流脉冲的正相位期间将足够的供电电压提供至一个或多个EEPROM。
图88为恒定电流脉冲波形1610形式的控制信号的一个方面的图形表示,所述恒定电流脉冲波形可由如图10中所示发生器102的信号调节电路202生成。时间沿横轴显示,单位为毫秒(ms);电流沿纵轴显示,单位为毫安(mA)。在图88所示的实施例中,位于发生器102侧面处的电流源发生器产生+/-15mA的周期性恒定电流脉冲1612,1614,所述周期性恒定电流脉冲各自具有显示为正转变1612a,1614a的第一相位和显示为负转变1612c,1614c的第二相位。电流源发生器经由缆线112,128联接到外科装置1600/控制电路1602的HS/SR输入端子。可采用其他恒定电流幅值。在例示的实施例中,控制电路1602既使用脉冲极性来检测开关SW1,SW2,SWn的最多2n个独特组合,还支持与单线EEPROM的通信。
图88A为图88的恒定电流脉冲波形1610形式的控制信号的一个方面的图形表示,示出了根据一个示例性实施例的波形1610的各种特征的数值。在图88A的示例性实施例中,横轴上的时间以毫秒(ms)示出,而沿纵轴的电流以毫安(mA)示出。另外,在图88A的示例性实施例中,电流脉冲1612,1614可具有+/-15mA的幅值。
应当理解,虽然电流脉冲被表征为具有为正转变的第一相位和为负转变的第二相位,但本公开的范围包括其中电流脉冲被表征为具有相反极性的实施例。例如,电流脉冲可被表征为具有为负转变的第一相位和为正转变的第二相位。还应当理解,对本文所公开控制电路中任一者的部件的选择可适当地被修改和配置成使用被表征为具有为负转变的第一相位和为正转变的第二相位的电流脉冲进行操作。另外,虽然本公开将控制信号描述为差分电流脉冲,但本公开的范围包括其中控制信号被表征为电压脉冲的实施例。因此,本发明所公开的控制电路的实施例不限于结合图88所述的差分电流脉冲的上下文。
现在参照图87和图88,在一个实施例中,控制电路1602与由开关SW1,SW2,SWn配置的并联电阻器R1,R2,R3和Rn+1一起以差分脉冲工作。另外,高速数据通信通过晶体管M1提供至所述至少一个存储器装置1604。在一个实施例中,控制电路1602使用由一个或多个按钮开关SW1,SW2,SWn的闭合所指定的可变电阻。电流脉冲1612,1614的正沿1612a,1614a和负沿1612c,1614c均用于获得测量,所述测量将允许在预先确定的范围内对未知串联缆线112,128和开关SW1,SW2,SWn触点的污染电阻进行补偿。最初正电流脉冲1612a对栅极电容器C2充电,随后负电流脉冲1612c使晶体管M2能够导通短暂的时间段,所述时间段由栅极电容器C2和电阻器R4的RC时间常数限定。在负电流脉冲1612c的第一相位期间,晶体管M2被置于饱和状态,从而在端子HS/SR之间产生通过外科装置1600的极低阻抗路径。在由R4和C2对的RC时间常数所限定的时间段之后,栅极电容器C2通过电阻器R4放电,并且晶体管M2的FET通道断开,导致总电流基于按钮开关SW1,SW2,SWn的状态被引导穿过电阻器R1,R2,R3,Rn+1路径。在晶体管M2处于闭合(饱和模式)时的低阻抗状态和在晶体管M2处于断开(截止模式)状态时的电阻器网络R1,R2,R3,Rn+1的状态为时间域中的两种用于检测按钮开关SW1,SW2,SWn的启动的阻抗状态。这提供了通过比较两种状态之间的不同来补偿外部路径电阻(手持件触点、布线、连接器电阻)的能力。
往回参照图88,开关SW1,SW2,SWn的组合的每一个在电流脉冲的负相位期间生成呈现给发生器102处的ADC的独特电阻。从发生器102传输至外科装置1600的恒定电流脉冲1612,1624将独特电压返回给发生器102中的ADC,所述独特电压与由开关SW1,SW2,SWn选择的电阻成比例。晶体管M1栅极电容器C2在正电流脉冲相位1612a,1614a期间充电。当电流脉冲波形在1612b,1614b处从正变化为负时,栅极电容器C2上的电压将晶体管M2导通,该电压有效地使端子HS/SR之间的外科装置1600控制电路1602短路。该短路仅存在短持续时间,该短持续时间由时间常数设定,且该时间常数通过电阻器R4和联接到晶体管M2栅极的栅极电容器C2限定。在栅极电容器C2已通过电阻器R4完全放电之后,控制电路1602转变为代表按钮开关SW1,SW2,SWn的状态的阻抗。在晶体管M2处于开路状态和短路状态时的每个时间段使用这两个测量,允许控制电路1602系统容忍由于缆线布线影响、连接器接触电阻和按钮开关电阻所致的电阻变化。此外,如先前所述,使用p-通道MOSFET晶体管M1而不是二极管是在不对手动开关检测能力产生不利影响的情况下促进高速EEPROM通信的有效手段。
图89为与图88中示出的控制信号的该方面相关联的各种检测区域的图形表示1620。时间沿横轴显示,单位为“mS”;阻抗沿纵轴显示,单位为“kΩ”。在图形表示1620中示出了五个检测区域(1-5)。还参照图87和图88,区域1表示在电流脉冲1612的负相位1612c期间当晶体管M2处于饱和模式时的状态,该状态产生通过外科装置1600的低电阻路径。这是表示除了按钮开关SW1,SW2,SWn检测电阻之外的串联电阻器R1的基线ADC测量。区域2表示在栅极电容器C2已通过电阻器R4完全放电由R4和C2限定的时间常数之后晶体管M2的状态。在区域2中,外科装置1600将呈现表示独特按钮开关SW1,SW2,SWn状态的电阻。区域2中的幅值根据按钮开关SW1,SW2,SWn的状态而改变。区域3表示当晶体管M2从饱和模式转变为截止模式时的欧姆区域。区域4表示对联接到晶体管M2栅极的栅极电容器C2进行充电的电流脉冲1612的上升正沿1612a。其阳极也联接到晶体管M2栅极的二极管D3允许栅极电容器C2被快速充电,以便不超过预先确定的总时间。区域5表示当晶体管M2从截止模式转变为饱和模式时电流脉冲1612的下降沿或负沿1612c。
图90为在SW1闭合且缆线/连接器112,128阻抗为0欧姆的发生器102处测量的电流脉冲波形1630形式的控制信号的一个方面的图形表示。电流脉冲波形1630示出之后是第二电流脉冲1634的第一电流脉冲1632。联接到晶体管M2栅极的栅极电容器C2在初始正沿1632a期间充电。在电流脉冲1632的负沿1632b期间,晶体管M2进入饱和(导通)状态,从而在端子HS/SR之间产生在外科装置1600之外的极低阻抗。在第一样本周期1636期间,ADC进行第一“基准”阻抗测量,其在波形1630上被标记为“ADC_NEG1”。在由R4和C2所设定的时间常数所限定的时间段T以后,栅极电容器C2通过电阻器R4放电并且晶体管M2的FET通道断开,导致总电流因为SW1处于闭合位置而被引导穿过电阻R1和R3的并联组合(R1||R3)。因此,在晶体管M2处于截止状态时,外科装置1600之外的阻抗由ADC在第二样本周期1638期间测量,并在波形1630上被标记为“ADC_NEG2”。第三样本周期1639可保留用于传统器械检测并在电流脉冲1634的后续正沿1634a之后发生,并被标记为ADC_POS。
图90A为图90的电流脉冲波形1630形式的控制信号的一个方面的图形表示,示出了根据一个示例性实施例的波形1630的各种特征的数值。时间沿横轴显示,单位为“mS”;ADC计数沿内部纵轴显示,并且ADC Vin沿外部纵轴显示,单位为伏特(V)。
图91为使用发生器102和控制电路1602实际测量的ADC输入波形1640的示波器描迹。时间沿横轴显示,单位为“ms”;ADC Vin沿纵轴显示,单位为伏特(V)。图90所示的实际波形1640形状非常类似于图90所示的模拟波形形状1630。
图92示出控制电路1702的另一个实施例,所述控制电路包括并行切换电阻电路和包括至少一个存储器装置的至少一个数据元件。在一个实施例中,控制电路1702可被差分电流脉冲形式的控制信号操作。如先前相对于图87所示的控制电路1602所述,控制电路1702与电流源(发生器)相接,所述电流源以+/-15mA输出周期性正向恒定电流脉冲和负向恒定电流脉冲,例如,如图88所示。控制电路1702设计既利用脉冲极性以检测最多2n个独特开关组合,还支持与一个或多个存储器装置1704(诸如单线EEPROM)的通信。
在一个实施例中,控制电路1702可连接至发生器102,以从信号调节电路202(例如,从图10所示的发生器端子HS和SR经由缆线112,128的导体对)接收询问信号(例如,预先确定的频率(诸如2kHz)的双极性询问信号)。控制电路1702可联接到预先确定数量的n个开关,以提供对外科装置1700(例如,超声装置104、电外科装置106、或组合的超声装置104/电外科装置106)的构型和/或操作的指示。图92所示的控制电路1702在结构和操作方面基本上类似于结合图87-91所述的控制电路1602,不同的是将晶体管M1替换为二极管D4。另外,两个控制电路1602和1702以基本上类似的方式运行。
如图92所示,在电流脉冲的正相位期间(如图88所示),二极管D2反向偏压并且二极管D4正向偏压,以允许栅极电容器C2通过二极管D3充电。在电流脉冲的负相位期间,二极管D4反向偏压并且二极管D2正向偏压,以将电阻器R1,R2,R3,Rn+1以由开关SW1,SW2,SWn的状态所确定的构型并联连接。在电流脉冲的负相位的初始期期间,晶体管M2由于充电的栅极电容器C2上的电压而处于饱和模式,并在等于由R4和C2所限定的时间常数的一段时期内将低阻抗路径提供给外部发生器102。在该时期期间,ADC进行如图90的波形1630中所示的初始阻抗测量“ADC_NEG1”。一旦栅极电容器C2通过电阻器R4放电,晶体管M2便截止并且ADC获悉由可通过对应开关SW1,SW2,SWn切换的电阻器R1和其他电阻R2,R3,Rn+1中的任一者的并联组合所配置的阻抗,如先前结合图87-91所述。检测区域与图89所示类似。
图93示出控制电路1802的一个实施例,所述控制电路包括串行切换电阻电路和包括至少一个存储器装置的至少一个数据元件。在一个实施例中,控制电路1802可被差分电流脉冲形式的控制信号操作。如先前相对于图87,92所示的控制电路1602,1702所述,控制电路1802与电流源(发生器)相接,所述电流源以+/-15mA输出周期性正向恒定电流脉冲和负向恒定电流脉冲,例如,如图88所示。控制电路1802既利用脉冲极性以检测最多2n个独特开关组合,还支持与一个或多个存储器装置1804,1806(诸如两个单线EEPROM)的通信。
在一个实施例中,控制电路1802可连接至发生器102,以从信号调节电路202(例如,从图10所示的发生器端子HS和SR经由缆线112,128的导体对)接收询问信号(例如,预先确定的频率(诸如2kHz)的双极性询问信号)。控制电路1802可联接到预先确定数量的n个开关,以提供对外科装置1800(例如,超声装置104、电外科装置106、或组合的超声装置104/电外科装置106)的构型和/或操作的指示。
在一个实施例中,控制电路1802使用可由最多n个按钮开关SW1,SW2,SWn配置的串联可变电阻。正电流脉冲和负电流脉冲两者都可用于获得测量,所述测量允许在给定范围内对未知串联缆线和污染电阻进行补偿。最初电流脉冲的正相位使二极管D2反向偏压并使二极管D4正向偏压,以将栅极电容器C2通过二极管D3充电。在电流脉冲的后续负相位期间,二极管D2正向偏压并且二极管D4反向偏压。因此,二极管D2现在将串联电阻器R1,R2,R3,Rn+1以由按钮开关SW1,SW2,SWn的状态确定的构型联接到发生器102中的外部ADC。在电流脉冲的负相位的第一部分期间,晶体管M2由于充电的栅极电容器C2上的电压而处于饱和模式,从而产生通过外科装置1800的极低阻抗路径。在由电阻器R4和C2设定的时间常数所限定的时间段之后,栅极电容器C2放电并且晶体管M2的FET通道断开,以将总电流引导穿过由电阻器R1,R2,R3,Rn+1限定的串联电阻器路径,该路径的构型由按钮开关SW1,SW2,SWn的状态确定。晶体管M2的初始短路状态和串联电阻器路径的后续阻抗状态为时间域中仅有的两种用于检测按钮开关SW1,SW2,SWn的状态的阻抗状态。这提供了通过比较这两种状态之间的不同来补偿外部路径电阻(手持件触点、布线、连接器电阻)的能力。检测区域与图89所示类似。
根据例如开关SW1,SW2,SWn的断开或闭合状态,信号调节电路202(例如,从图10所示的发生器端子HS和SR经由缆线112,128的导体对)将获悉不同的阻抗(例如,电阻)。对于例如其中n=3,并且控制电路1802包括三个开关SW1,SW2,SW3的实施例,存在可通过信号调节电路202基于开关SW1,SW2,SW3的状态检测的八个独特开关可配置阻抗,如以下表9所示:
横跨控制电路1802的HS/RS端子放置的双重保护二极管D1和D5用于钳制在外科装置1800连接到发生器102和从发生器102断开时来自外科装置1800和发生器102的ESD和/或瞬变。
图94示出了控制电路1902的一个实施例,所述控制电路包括具有精密基准电压的串行切换电阻电路和包括至少一个存储器装置的至少一个数据元件。在一个实施例中,控制电路1902可被差分电流脉冲形式的控制信号操作。如先前相对于图87,92,93所示的控制电路1602,1702,1802所述,控制电路1902与电流源(发生器)相接,所述电流源以+/-15mA输出周期性正向恒定电流脉冲和负向恒定电流脉冲,例如,如图88所示。控制电路1902既利用脉冲极性以检测最多2n个独特开关组合,还支持与一个或多个存储器装置1904,1906(诸如两个单线EEPROM)的通信。
在一个实施例中,控制电路1902可连接至发生器102,以从信号调节电路202(例如,从图10所示的发生器端子HS和SR经由缆线112,128的导体对)接收询问信号(例如,预先确定的频率(诸如2kHz)的双极性询问信号)。控制电路1902可联接到预先确定数量的n个开关,以提供对外科装置1900(例如,超声装置104、电外科装置106、或组合的超声装置104/电外科装置106)的构型和/或操作的指示。
在一个实施例中,控制电路1902使用可由最多n个按钮开关SW1,SW2,SWn配置的串联可变电阻。然而,图94中的控制电路1902包括用齐纳二极管D6实施的附加分路基准电压,其允许较高的电阻值用于开关检测。当不能维持低按钮接触电阻时(即,银墨柔性电路),较高的电阻值更为合适。在其他方面,控制电路1902在操作中基本上类似于结合图93所述的控制电路1802,不同之处在于开关可配置阻抗与电阻器R6并联。
根据例如开关SW1,SW2,SWn的断开或闭合状态,信号调节电路202(例如,从图10所示的发生器端子HS和SR经由缆线112,128的导体对)将获悉不同的阻抗(例如,电阻)。对于例如其中n=3并且控制电路1902包括三个开关SW1,SW2,SW3的实施例,存在可通过信号调节电路202基于开关SW1,SW2,SW3的状态检测的八个独特开关可配置阻抗,如以下表10所示:
图95示出控制电路2002的一个实施例,所述控制电路包括可变频率切换电阻电路和包括至少一个存储器装置的至少一个数据元件。如先前相对于图87,92,93,94所示的控制电路1602,1702,1802,1902所述,控制电路2002与电流源(发生器)相接,所述电流源以+/-15mA输出周期性正向恒定电流脉冲和负向恒定电流脉冲,例如,如图88所示。控制电路2002既利用脉冲极性以检测最多2n个独特开关组合,还支持与一个或多个存储器装置2004,2006(诸如两个单线EEPROM)的通信。
在一个实施例中,控制电路2002可连接至发生器102,以从信号调节电路202(例如,从图10所示的发生器端子HS和SR经由缆线112,128的导体对)接收询问信号(例如,预先确定的频率(诸如2kHz)的双极性询问信号)。控制电路2002可联接到预先确定数量的n个开关,以提供对外科装置2000(例如,超声装置104、电外科装置106、或组合的超声装置104/电外科装置106)的构型和/或操作的指示。
切换电阻构型控制电路2002使用可变脉冲频率以确定按钮开关SW1,SW2,SWn的状态。控制电路2002既利用脉冲极性以检测最多2n个独特开关组合,还支持与一个或多个存储器装置2004,2006(诸如两个单线EEPROM)的通信。使用可变频率允许由控制电路2002采用的检测方法与外部可变串联电阻无关。可将施密特触发器电路2008配置为RC振荡器,其中振荡的频率由RC时间常数确定,该RC时间常数通过按钮开关配置的电阻器R1,R2,R3,Rn+1和电容器C3设定。初始负电流脉冲对即将用作功率源的大容量电容器C4充电,以便在电流源脉冲之间续流。然后电流源发生器能够用于在频率测量期间的零位电流。输出脉冲通过C5电容性地联接返回到发生器比较器。由此,可处理振荡器频率以确定开关SW1,SW2,SWn
的状态。根据例如开关SW1,SW2,SWn的断开或闭合状态,信号调节电路202(例如,从图10所示的发生器端子HS和SR经由缆线112,128的导体对)将基于开关可选择电阻获悉不同的频率(fo)。对于例如其中n=3并且控制电路2002包括三个开关SW1,SW2,SW3的实施例,存在由基于施密特触发器2008的振荡器的RC时间常数确定的八个独特开关可配置频率,所述RC时间常数通过按钮开关配置的电阻器R1,R2,R3,R4和电容器C3设定。由信号条件调节电路202基于开关SW1,SW2,SW3的状态获悉的频率(fo)如下表11所述:
图96为检测方法的一个实施例的图形表示2010,示出了控制电路2002的检测区域,所述控制电路如结合图95所述包括可变频率切换电阻电路和存储器装置。时间(mS)沿横轴显示,并且电压(V)沿纵轴显示。如图96所示,区域1显示源于控制电路2001的基于RC的振荡器电路2008的发生器102比较器电路的脉冲输出。如表11所示,对于n=3,存在代表每个按钮开关SW1,SW2,SW3的状态的八个独特频率。区域2显示振荡器电路2008的大容量供给电容器C4,其正被负电流脉冲充电。区域3显示针对发生器102比较器输入的脉冲波形。
图97示出控制电路2102的一个实施例,所述控制电路包括具有精密基准电压的并行切换电阻电路和包括至少一个存储器装置的至少一个数据元件,所述存储器装置采用可变斜率波形来确定开关状态。在一个实施例中,控制电路2102可被差分电流脉冲形式的控制信号操作。如先前相对于图87,92,93,94,95所示的控制电路1602,1702,1802,1902,2002所述,控制电路2102与电流源(发生器)相接,所述电流源以+/-15mA输出周期性正向恒定电流脉冲和负向恒定电流脉冲,例如,如图88所示。控制电路2102既利用脉冲极性以检测最多2n个独特开关组合,还支持与一个或多个存储器装置2104,2106(诸如两个单线EEPROM)的通信。
在一个实施例中,控制电路2102可连接至发生器102,以从信号调节电路202(例如,从图10所示的发生器端子HS和SR经由缆线112,128的导体对)接收询问信号(例如,预先确定的频率(诸如2kHz)的双极性询问信号)。控制电路2102可联接到预先确定数量的n个开关,以提供对外科装置2100(例如,超声装置104、电外科装置106、或组合的超声装置104/电外科装置106)的构型和/或操作的指示。
控制电路2102采用可变斜率波形以确定按钮开关SW1,SW2,SWn的状态。恒定电流脉冲源驱使电流进入电容性负载(例如,电容器C6)中,以生成依赖于电容器C6的电容值的斜率。使用分路调节器D6和充电电容器的组合创建有源电路,该有源电路通过改变开关可配置电阻R1,R2,R3,Rn+1而不是改变电容C6来改变斜率。每个按钮开关SW1,SW2,SWn状态基于独特时间常数生成如图98所示的独特斜坡斜率,所述独特时间常数通过电容器C6和如由开关SW1,SW2,SWn所选择的电阻R1,R2,R3,Rn+1
的组合确定。根据例如开关SW1,SW2,SWn的断开或闭合状态,信号调节电路202(例如,从图10所示的发生器端子HS和SR经由缆线112,128的导体对)将基于独特时间常数获悉不同的斜坡斜率,所述独特时间常数基于开关可选择的电阻。对于例如其中n=3并且控制电路2102包括三个开关SW1,SW2,SW3的实施例,存在由RC时间常数确定的八个独特开关可配置斜坡斜率,所述RC时间常数通过按钮开关配置的电阻器R1,R2,R3,R4和电容器C6确定。由信号条件调节电路202基于每个开关组合SW1,SW2,SW3的状态获悉的斜坡斜率如下表12所述:
图98为检测方法的一个实施例的图形表示2110,示出了控制电路2102的检测区域,所述控制电路如结合图97所述包括可变斜坡/斜率切换电阻电路和存储器装置。时间(mS)沿横轴显示,并且ADC计数沿纵轴显示。区域1显示受时间常数控制的可变斜率,该时间常数通过电容器C6和开关SW1,SW2,SW3可配置电阻R1,R2,R3,R4确定。每个开关SW1,SW2,SW3状态提供唯一斜率。区域2为将RC时间常数重置的时间区域。模拟建模证实对极高耐接触腐蚀性免疫。然而,基于时间的测量由于信号传递的快速瞬变沿而易受缆线电感和电容的影响。因此,在本公开内设想了由于信号传递的快速瞬变沿的缆线电感和电容的补偿电路。斜率检测将错误检测开关状态的风险降至最低。可能需要电流脉冲的上升沿和下降沿慢于例如缆线的最低谐振频率。然而,所述实施例不限于该上下文。
图99示出了包括单线多开关输入装置的控制电路2202的一个实施例。如先前相对于图87,92,93,94,95,97所示的控制电路1602,1702,1802,1902,2002,2102所述,控制电路2202与电流源(发生器)相接,所述电流源以+/-15mA输出周期性正向恒定电流脉冲和负向恒定电流脉冲,例如,如图88所示。控制电路2202既使用脉冲极性来检测最多2n个独特开关组合,还支持与一个或多个存储器装置(例如,两个单线EEPROM)的通信,出于简洁和清晰的需要,所述一个或多个存储器装置未在图99中示出,但是其可包括在该实施例的各方面中。另外,出于简洁和清晰的需要,双向功率的二极管对D2/D4未在图99中示出,但是其可包括在该实施例的各方面中。
在一个实施例中,控制电路2202可连接至发生器102,以从信号调节电路202(例如,从图10所示的发生器端子HS和SR经由缆线112,128的导体对)接收询问信号(例如,预先确定的频率(诸如2kHz)的双极性询问信号)控制电路2202可联接到预先确定数量的n个开关,以提供对外科装置2200(例如,超声装置104、电外科装置106、或组合的超声装置104/电外科装置106)的构型和/或操作的指示。
在一个实施例中,控制电路2202的单线多开关输入装置使用单线端口扩展装置2204,诸如以商品名“1-Wire”为人所知的得自CA,Sunnyvale的Maxim IntegratedProducts,Inc.的Maxim DS24088-通道、可编程I/O单线集成电路,或其等同物。端口扩展装置2204可由发生器102的负电流脉冲供电。端口扩展装置2204遵守单线通信协议,以适应最多八个开关输入2208。端口扩展装置2204输出被配置为漏极开路,并提供最大100Ω的导通电阻。稳健的通道存取通信协议确保输出设定改变无误地出现。数据有效频闪输出可用于将端口扩展装置2204逻辑状态锁存进外部电路诸如D/A转换器(DAC)或微控制器数据总线中。端口扩展装置2204选择八个开关SW1-SW8中的一个,以选择电阻器组2210中的八个对应电阻器1-8中的一个。在一个实施例中,例如,检测方法包括使用控制电路2202的单线通信协议,利用用于读取外科装置2200EEPROM的同一个软件功能来读取开关SW1-SW8状态中的任一个。在其他实施例中,可将控制电路2202扩展以读取额外的开关输入。在一个实施例中,可使用循环冗余码(CRC)错误检查,以消除或最小化开关状态的不确定性。可能的是单线通信可能易受来自其他电外科器械的启动噪声的影响,因此,在本公开内设想了将来自此类电外科器械的干扰最小化的补偿电路和技术。
虽然文中结合某些公开的实施例对装置的多种实施例作了描述,但这些实施例的许多修改和变化形式也可被实现。例如,可采用不同类型的端部执行器。另外,在公开了用于某些部件的材料的情况下,均可使用其他材料。上述描述和以下权利要求旨在涵盖所有此类修改和变型。
以引用方式全文或部分地并入本文的任何专利、专利公开或其他公开材料均仅在所并入的材料不与本发明所述的现有定义、陈述或其他公开材料相冲突的范围内并入本文。由此,在必要程度下,本文所明确阐述的公开内容将会取代以引用的方式并入本文中的任何相冲突的材料。如果据述以引用的方式并入本文但与本文所述现有定义、陈述或者其他公开材料相冲突的任何材料或其部分,仅在所并入的材料与现有公开材料之间不产生冲突的程度下并入本文。
Claims (7)
1.一种外科装置,该外科装置包括:
用于作用在组织上的端部执行器;和
被配置成能够与外科发生器通信的控制电路,所述控制电路包括:
与所述外科发生器通信的导体对;
第一电路部分,所述第一电路部分包括:
被配置成能够在打开状态和闭合状态之间转换的第一开关;
与所述第一开关并联的第一电阻器;
被配置成能够在打开状态和闭合状态之间进行转换的第二开关;
与所述第二开关并联联接的第二电阻器,其中,所述第一开关和第一电阻器的组合与所述第二开关和第二电阻器的组合串联联接;
与所述第一电路部分并联联接的基准电压,其中,所述控制电路被配置成能够从所述发生器且通过所述导体对接收询问信号,其中,所述第一开关和第二开关中的至少一者的状态由所述询问信号的至少一种特性确定;
与所述第一电路部分并联联接的电容器;
与所述第一电路部分串联联接的电阻器;和
联接至所述第一电路部分的存储器装置。
2.根据权利要求1所述的外科装置,其中所述第一开关的状态能够基于所述电容器上的电压斜率确定。
3.根据权利要求1所述的外科装置,包括与所述第一开关和所述第二开关中的至少一个开关连通的振荡器,其中所述第一开关和所述第二开关中的所述至少一个开关的状态能够基于所述振荡器的频率确定。
4.根据权利要求1所述的外科装置,包括联接到至少一个开关的单线多开关输入装置,其中所述至少一个开关的状态能够通过单线通信协议被传送至所述发生器。
5.根据权利要求1所述的外科装置,其中所述询问信号为具有正相位和负相位的差分恒定电流脉冲。
6.根据权利要求1所述的外科装置,其中所述存储器装置包括至少一个单线电可擦可编程只读存储器(EEPROM)。
7.根据权利要求5所述的外科装置,其中所述询问信号的正相位为差分恒定电流脉冲的正转变,并且所述差分恒定电流脉冲的负相位为差分恒定电流脉冲的负转变。
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PCT/US2013/036568 WO2013158537A2 (en) | 2012-04-16 | 2013-04-15 | Surgical generator for ultrasonic and electrosurgical devices |
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BR112014025700A8 (pt) | 2021-05-25 |
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BR112014025700B1 (pt) | 2022-06-07 |
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MX342019B (es) | 2016-09-08 |
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US20160089533A1 (en) | 2016-03-31 |
US20120265196A1 (en) | 2012-10-18 |
WO2013158537A2 (en) | 2013-10-24 |
AU2013249506B2 (en) | 2017-11-23 |
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