CN1274566A - 电外科系统和仪器 - Google Patents
电外科系统和仪器 Download PDFInfo
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- A—HUMAN NECESSITIES
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- A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
- A61B18/04—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating
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Abstract
在具有射频发生器和带有治疗电极的仪器的电外科系统中,该发生器包括用于感测来自电极的热离子发射的电路,作为控制对该电极提供的射频能量的装置。热离子发射是通过使用具有隔离输出端的检测器检测在发生器的输出端的直流电压而感测的,并且发生器输出功率被控制为把直流电压限制为预定阈值。相应地,该电极的温度可以被限制以避免电极损坏,本发明还具有减小由于电外科治疗而造成的神经刺激。
Description
本发明涉及电外科系统、电外科仪器和完成电外科手术的方法。
采用具有被提供射频电压的一个或多个电极的尖端的仪器进行生物组织的电外科切割和切除通常造成细胞的破裂,这是有源电极和被治疗的生物组织之间的电弧产生的结果,或者在水下电外科手术的情况中,这是有源电极与覆盖被治疗的生物组织的导电液体之间的电弧产生的结果。如欧洲专利EP-A-0754437中所述,如果足够的射频功率被施加到一电极上,可能出现电极损坏,以造成电极材料的燃烧或熔化,并且这可以通过感测峰值电极电压并且施加反馈以减小所施加功率而避免,从而设置峰值电压。应当理解对于给定的功率设置,电极的温度取决于散热的速率,而散热速率反过来取决于这样的变量,例如生物组织接合程度、电极结构、以及在电极周围流动的流体。从而,为了避免电极损坏,该峰值电压极限必须被设置在足够低的电平,以避免在最坏的散热情况中的损坏,即,当没有冷却流体和/或电极被生物组织所包住的情况下。
已知在该电极处的电弧可以造成神经刺激。这是由于当电极被加热时的热离子效应所造成的。由于在发生器中的射频源与该电极之间使用耦合电容器是强制性的,因此该电极被隔离,允许电荷在电容器上累积,这在电极接触生物组织时或导电流体覆盖该生物组织时产生神经刺激。
本发明基于这样的认识,即热离子效应是取决于温度的,因此,可以被用作为电极温度的指示。相应地,本发明提供一种包括发生器的电外科系统,该发生器包括用于馈送到电外科仪器的治疗电极的射频能量源,其中该发生器包括用于感测发自该电极的热离子发射的电路。
本发明还包括一种电外科系统,其中包括:包括射频能量源的发生器,以及耦合到该发生器并具有治疗电极的电外科仪器,其特征在于该系统包括:直流电压检测器,其被设计为检测在治疗电极上超过2伏的直流补偿;以及耦合到该检测器并响应该直流补偿用于控制施加到该仪器上的射频能量的控制电路。这种方式,在治疗电极处的直流电压电平由于热离子效应可以被限制为一个平均值,例如,控制电极温度平均值。确实,根据本发明,热离子效应与电弧之间的关系,特别是与在这样一个电平以及在这样治疗电极变的非常热的环境下的电弧之间的关系可以被用于电极过热保护。这反过来允许电极在散热最差的情况下用于比使用现有电压感测技术更高的温度中,从而增加生物组织被切割或切除的速率。
一般地,对于过热保护,控制电路和检测器把直流补偿限制到从50V到100V的范围中的一个预定直流电压电平。在实践中,实际电压电平取决于电极结构和电极材料。因此,如果使用铂电极,电压极限被设置为当使电极达到铂的熔点1600度时的电极电压。
另外,最大直流补偿电压可以被设置为相当低的数值,以减少在敏感位置的神经刺激,例如在神经外科中对脊髓和在肌肉组织做手术。
在本明的优选实施例中,发生器具有可连接到治疗电极的输出端,并且检测器具有(i)连接到该输出端的检测输入端,以及(ii)把该检测器连接到控制电路的隔离装置。通过具有耦合到发生器输出端的电源电路并且包括用于整流施加到该输出端的射频电外科信号,该检测器可以被从发生器的射频输出能量供能。由于热离子效应直到射频输出电压到达产生电弧的电平时才出现,因此这是许可的。因此,检测器在较低电压下不工作的事实不是不利因素。一般地,为了实现在检测器输出端的隔离,其包括用于产生表示直流补偿的交流测量信号,并且该隔离设备包括耦合到接收该交流测量信号并且把其馈送到控制电路的光隔离器。优选的检测器还包括反极性直流补偿检测器,作为故障状态指示器,例如当在导电流体区域使用双极型电极组件中流体的缺乏造成直流电极反向时,该指示器被用于使射频源不启动。
根据本发明第二方面,电外科发生器包括射频能量来源、有源输出端、返回输出端以及在该来源与有源输出端之间的直流隔离电容器,该发生器具有直流补偿检测器,该检测器具有连接在隔离电容器的输出端一侧用于检测超过2伏的直流电压的旁路输入端,该发生器还具有控制电路,其耦合到该能量源,用于响应在旁路输入端处的直流补偿电压控制施加到有源输入端的射频能量。
根据本发明第三方面,一种执行电外科的生物组织切割或切除的方法,其中包括把射频能量施加到电外科仪器,以在该仪器的治疗电极处激励电弧,并且根据由于来自电极的热离子发射而在电极获得的直流电压来调节所施加能量的电平。射频能量可以被调节为使电极的温度最大,而基本上不损坏电极,这一般是通过把直流电压限制为小于100V的阈值而实现的。
在上述优选实施例中,作为在发生器的输出级电容器通过高值电阻连续放电的结果,检测到热离子效应出现,所检测的电极上的直流电压表示该效应。由于检测效应是由在输出级中电容器放电的时间长度所限制的,这具有相对较慢响应时间的缺点。该时间常数是该电路中电容与电阻的乘积。电容器需要较大以减小输出阻抗,并且跨过输出端连接的旁路电阻较大,以避免大的直流电流流过病人。
另一个实施例提供用于检测来自有源电极的热离子发射,其中被热离子发射所影响的交流现象被检测,不需要跨过发生器输出端的直流导电路径。相应地,本发明另一个方面提供一个调制发生器输出,以及耦合到该发生器输出的检测电路,通过耦合而不包括任何直流导电路径,该检测电路被调谐为发生器输出的调制的频率,其中在检测电路中,来自有源电极的热离子发射引起在发生器输出端的调制现象。
在优选实施例中,发生器输出的幅度被按照这样的方式调制,使得在没有任何热离子效应时,被测量的发生器输出在发生器输出的单个周期上的平均值保持恒定;热离子发射的存在使得所测量发生器输出在单个周期上的平均值在发生器幅度调制的频率上变化,并且在平均值中变化的幅度对应于热离子效应的程度。检测电路可以由适当调谐的谐振电路和检测器所提供,该检测器电感耦合到发生器输出级,以检测在谐振电路中由于热离子发射所造成的电压。
现在将参照附图,通过实例描述本发明,其中:
图1为示出根据本发明的电外科系统的示意图;
图2为示出浸入在导电液体中使用的用于生物组织切除的电极部件的部分示图;
图3A和3B为包括直流补偿检测器的电外科系统的电路图;
图4为根据本发明的另一种电外科系统的电路图;
图5示出形成图4的系统的一部分的发生器的调制输出电压波形的波形图;以及
图6为示出在图4中所示的系统的有源电极处存在热离子效应时发生器输出波形的波形图,以及在输出电压的单个射频周期上平均的平均输出电压的波形。
本发明可应用于湿和干区域的电外科的手术。参照图1,该系统包括具有输出插座10S的发生器10,其通过连接芯线14以机头12的形式提供用于电外科仪器的射频输出。发生器的启动可以从机头12通过控制连接芯线14而执行,或者通过脚踏开关16而执行,如图所示,该脚踏开关通过脚踏开关连接芯线18分离连接到发生器10的后部。在所示实施例中,脚踏开关单元16具有两个脚踏开关16A和16B,用于分别选择发生器的干燥模式和汽化模式。发生器前面板具有按键20和22,用于分别设置干燥和汽化功率电平,其被在显示器24上表示。按键26被提供作为用于模式选择的另一种方式。
机头12安装在具有双电极结构的可拆卸电极组件28上,如图2的部分示图所示。
图2为电极组件28末端的放大示图。在其末端,该组件具有有源电极30,其在本实施例中形成为连接到中央导体32的线圈。该线圈由铂所制成。返回电极36在有源电极30附近,并且由在径向和长度方向上延伸的陶瓷绝缘体所隔开。该返回电极36绕着内部导体32同轴分布,作为套筒,其作为向着组件28(参见图1)的近端延伸的空心轴,在此它被在机头12中连接到连接芯线14中的导体。类似地,内部导体32延伸到机头12并且连接到芯线14中的另一个导体。内部导体32与返回电极36之间的绝缘由绝缘体34提供,该绝缘体构成为在返回电极内延伸的套管,其使得返回电极36与有源电极30的内部延长部分(未示出)相绝缘。为了使有源电极处的功率密度比返回电极更大,返回电极的表面积比有源电极大得多。对于典型尺寸,在电极组件的末端,返回电极的直径一般在从1毫米到3毫米的范围内,返回电极的暴露部分的纵向延伸一般在1毫米和5毫米之间,并且与有源电极纵向间隔在1毫米和5毫米之间。该电极组件28具有覆盖轴40的绝缘套管42,并且在陶瓷绝缘体34附近终止,以使得轴40的末端暴露成为返回电极36。
在作为用于在导电流体区域切割或切除生物组织的仪器中,电极组件28如图2中所示施加到要被治疗的生物组织44,手术位置被浸入在生理盐水(0.9%w/v)溶液46中,该溶液中浸入有源电极30和返回电极36。
电极组件是双极型的,仅有一个电极(有源电极30)轴向延伸到该装置的末端。在通常情况下,这意味着返回电极在湿区域中保持与被处理的生物组织相隔离,并且通过与该返回电极相接触的导电液体,一条电流路径存在于生物组织与该返回电极之间。只要考虑双极型电外科能量,该导电液体46被认为是生物组织的低阻抗延伸。
当足够的射频电压被施加在电极30、36之间,在导电液体46中的功率耗散造成液体汽化,在有源电极30的表面上开始形成小的气泡,该气泡最终相结合,直到电极被完全包在蒸汽50中。蒸汽包50被有源电极30与蒸汽-盐水界面之间跨过蒸汽包的放电52所保持。现在,由于有源电极发热的结果,主要的功率耗散出现在该汽包中,能量耗散的量是所传送功率的一个函数。通过使该有源电极30保持接近该生物组织44的表面,如图2中所示,使得蒸汽包截断生物组织表面,由于在电极与生物组织之间出现电弧,通过使细胞破裂而进行生物组织切除。
该工作模式可以在相对较宽的功率电平范围内被保持,但是增加该传送功率超过该范围使得电极温度快速上升,对该电极造成潜在的损坏。出现这种情况的功率点取决于从该电极散热的速度,可以理解这受到流体46流过电极20的对流、电极30与生物组织的接近程度所影响,在最坏情况中,电极30埋在生物组织中。随后,当峰值电压极限可以被建立以避免在电极处温度持续上升,这种将生效的极限必须被设置在一个电平,其将避免在最坏的散热条件下温度上升。
根据本发明,射频功率传送到该电极是通过感测该电极的温度而控制的。这是间接通过监控热离子效应而实现的,该热离子效应将参照图3A和3B进行描述。
参照图3A,根据本发明的系统包括在第一和第二输出端64、66之间通过耦合电容器62、63传送电外科电压的射频电压源60,电外科仪器的有源和返回电极分别连接到该第一和第二输出端。当在有源电极出现电弧时,如图2中所示,当该电极与生物组织44相分离时,出现来自该电极的热离子发射,这取决于电极的温度,导致在有源输出端64上产生正电势。实际上,加热的有源电极32、生物组织、导电流体和返回电极一同作为整流器,导电溶液作为整流器的阳极,并且有源电极作为整流器的阴极。有源电极越热,则整流作用越大并且在发生器的输出端64上的直流补偿电压越大。
利用具有输入电路的检测器监控取决于温度的正电势(直流补偿电压),该输入电路具有耦合到输出端64的串联射频扼流圈68、以及耦合到公共干线71的平滑电容器70,其连接返回端66。因此在有源输出端64的电压的直流分量在扼流圈68和平滑电容器70的接点处累积,在此处该直流分量被施加到分压器72、74,其具有至少2M次的输入阻抗,一般在50和100M次之间。分压器72、74的输出被施加到高阻抗缓冲器76,其输出把一个驱动信号提供给压控振荡器(VCO)78。提供在50到100M次毓围中的输入阻抗对于50到100V范围中的直流补偿产生1μA的检测电流。保持较低检测电流的优点是避免由于目标生物组织和返回电极之间的直流电而造成的神经刺激。
在VCO 78中把直流补偿电压轮换成交流信号使得补偿电压电平的信号表示通过光隔离器82发送到连接检测器的输出端80的隔离控制电路(未示出)。因此,直流补偿的表示通过发生器的输出端与功率产生和控制电路之间的安全隔离阻挡器传输。在控制电路中,利用单稳态和低通滤波器,交流信号可以被转换回直流电平,或者可以由闸门式计数器所计数并被数字转换。在另一种情况中,控制电路被设计为当直流补偿电压到达预定值(一般在50到100V的范围内)时,减小电源60的电压。按这种方式,通过选择与有源电极的最大安全工作温度相关的阈值直流补偿电压,被传送到有源电极的射频功率可以在不同散热条件下最大化。
当图2中所示的双极型电极组件被错误使用时,例如当在该组件周围没有足够的盐水时,有可能在返回电极36处产生电弧。在这种情况下,直流补偿极性反转,使得有源端64相对于返回端变为负电平。图3A中所示的检测器包括反极性检测电路,其形式是比较器86旁路VCO 78,并且具有耦合到例如“或”门86的一个输入端的输出,“或”门的另一个输入端接收来自VCO 78的交流输出。比较器84的另一个输入端耦合到负电压基准。通常,比较器84的输入较低,这意味着由VCO所产生的交流信号通过“或”门84到达光隔离器82。但是,当在发生器的输出端64上的直流补偿电压变负,这不取决于施加到比较器84的负基准电压,比较器84的输出变高,并且“或”门86阻挡来自VCO 78的交流信号,并且缺少从检测器输出端80施加到控制电路的交流信号可以被用作为关闭射频电压源60的故障指示信号。
在该实施例中,用于缓冲器76、VCO 78、比较器84和“或”门86的功率被从传送到发生器的输出端64和66的射频电压本身得出,避免需要另外的隔离阻挡器。用于该目的的适当电源在图3B中示出。耦合在发生器输出端64和66之间的降压变压器90驱动桥式整流器92,以跨过平滑电容器96传送在电源输出端94的直流电压。变压器90的次级线圈与中央抽头连接到返回输出端66,并且检测器的公共干线被提供有双极型电源,以允许正向和负向直流补偿电压。按这种方式从射频输出导出功率的事实导致检测器在低电压下不能工作,这是有利的,因为直到发生器的射频输出电压到达在有源电极产生电弧的电平时,依赖于控制激励的热离子辐射才会发生。
现在参照图4,其中概略地示出根据本发明的交流发生器110,其连接到具有有源电极130和返回电极136的电外科仪器。发生器的输出级包括一对耦合电容器162、163,其避免在射频源与电极130、136之间通过发生器输出端164、166产生直流通道。另外,发生器输出级包括分别与有源和返回电极130、136相串联的电感器168。
参照图5,发生器的输出幅度(即在输出端164、166出的峰—峰值输出电压)被调制,在本实例中,提供一个发生器输出信号,其具有500kHz的输出频率并且在25kHz的频率下被幅度调制。自然,可以采用其它发生器和调制频率。在有源电极136没有任何热离子效应时,发生器输出电压相对于零电压线对称,即,因为在发生器输出端的单个时间周期上,最大正输出电压的电压数值相对于零基准电压的增加与最大负输出电压中的相应增加相一致,在发生器输出的单个调制周期上测量的发生器输出信号的平均数值为常数。
但是,一旦在有源电极出现过度加热,以造成来自有源电极的电子的热离子发射,在此具有从有源电极到返回电极的电子净流量。因此,从返回电极(其作为阳极)到有源电极具有净流量电流(因为电流的方向被定义为正电荷的流动方向)。现在参照图6,具有在一个方向上位移调制发生器输平均出电压波形的效果,在此为正方向,使得除了具有输出电压之外,在单个周期的平均电压以非线性的方式保持在零伏特,在电极处的热离子效应造成发生器输出的部分整流,并且在单个周期上测量的平均输出电压现在为非零电压。该电压的幅度在幅度调制的频率(在本实例中为25kHz)上变化。在平均输出电压中的变化由图6中的线VAV所表示。另外,平均输出电压中变化的幅度A取决于在发生器输出中正位移的程度,25kHz信号的最大幅度是幅度调制的深度的两倍。幅度A是从返回电极到有源电极的净电流的测量,因此,反过来,在有源电极的热离子效应的测量是有源电极温度的测量。
再次参照图4,为了检测在平均输出电压中25kHz值的变化,该变化作为热离子效应的结果,发生器包括具有调谐为调制频率(在此为25kHz)的谐振电路172、174,并且包括交流电压感测级176。该谐振电路是并联谐振,其电感器174电压耦合到输出级串联电感器168,形成隔离变压器的电感器在直流上使感测电路与输出端164、166相隔离。当在有源电极130没有热离子效应时,在此没有到发生器输出端的净25kHz分量,因为基本发生器输出在500kHz的发生器工作频率上为正弦波,其在工作频率的单个周期上测量的平均电压值恒定保持在零伏。一旦发生热离子发射,在发生器输出中的正位移在平均发生器输出中导入25kHz分量,在平均数值中变化的25kHz的幅度被在交流电压感测级176中检测,其输出如上文所述直接表示在有源电极130处的热离子效应的程度,因此,表示有源电极130的温度。
在调制中(未示出),谐振电路可以在发生器输出电路本身中,例如,作为串联的并联谐振电路,其中包括电感器168以及与其并联的电容器。该电压感测级可以通过电感器168耦合到谐振电路,以检测跨过该谐振电路的调制电压。
电压感测级176的输出耦合到反馈电路(未示出),其改变绝对发生器输出幅度(例如,发生器输出的最大或最小幅度,而不是幅度调制的程度或深度),以在有源电极保持给定的预定温度。
理想地,调制的频率被选择,使得来自有源电极的热离子发射中的改变速度与单个调制周期或循环相比较慢。在25kHz的调制频率处,调制周期是40毫秒,其明显地比上述参照图3A和3B描述的实施例的直流耦合检测电路的响应时间更短。
在发生器输出电压中调制的深度(即,幅度或程度)理想地根据要被检测的热离子发射的大小而选择。在发生器输出中的幅度调制的相对大的深度具有这样的结果,即使在发生器输出中小的位移或偏移将导致在工作频率的单个周期上测量的发生器输出的平均值的明显变化,这将允许容易地检测相对较小的热离子发射。在实践中,由热离子效应所导致的平均电压的位移在50V的区域中,在工作频率处的峰一峰输出电压一般为1000V。
所示的发生器输出级实际上是谐振电路,其谐振频率随着在电极130、136上的负载的阻抗而变化。如果发生器输出级的谐振频率相对于工作频率位移到这样的一种程度,即在发生器输出电压中的具有比幅度调制的深度更大的电压降,其在比发生器输出的单个调制周期的持续时间更短的时间段中出现,幅度调制随着幅度中的相对较大变化而显著改变,它的出现是变化谐振的结果。如上文所述,对于热离子发射的给定电平,由伏特计级176所检测的电压的幅度来说是发生器输出的调制深度的函数,这实际上是由于输出级谐振中的变化所造成的这种调制深度中的不相关变化,它造成由伏特计176对热离子发射测量中的不准确。换一种说法,尽管在单个周期上测量的发生器输出的平均值中的变化将表示热离子发射的存在,这种变化的幅度不必然表示这种发射的程度,因为由于发生器的输出级中的变化谐振的结果具有造成调制深度的变化的可能性。
由于输出电路的谐振频率随着负载阻抗而变化,不可能简单的预先解决谐振中的变化,因为不可能预先知道在何时或者在何种频率有可能发生谐振的变化。相应地,在图4系统中的发生器包括补偿电路结构,其中包括用于使来自伏特计176的输出标准化的调制基准。再次参照图4,该补偿电路结构具有跨过发生器输出变压器182的初级线圈连接的检测电路180。该调制检测电路180包括与电阻器196和电容器188相串联的二极管184。伏特计和另一个电阻器191与电容器188相并联,并且伏特计190检测在发生器输出中的调制瞬时深度,并且通过来自感测电路的伏特计170的输出可以被有效地标准化,以仅仅反映在电极130处的热离子发射的效应,这可以被用于提供调制基准。
本发明的使用不限于湿区域(水下)电外科手术。在干区域外科手术中作用单极或双极电外科仪器还会出现电弧,并且按照与上文所述相同的方式,功率可以利用热离子效应而控制。这还有可能把直流补偿阈值电压设置在相对较低的电平,以充分避免在有源电极断续的接触生物组织的位置产生神经刺激。
在单极应用中,电弧的强度取决于在产生电弧位置和返回电极之间的导电路径的阻抗,低阻抗增加峰值电弧电流以及温度、切割速率和神经刺激。随后根据利用热离子效应感测的电极温度控制功率(以便于降低电极温度中的变化)以实现更加连续的生物组织手术。这可以导致切割质量的增加,例如,在于生物组织破坏和在切割位置附近的烧焦形成与仅仅依赖于电压控制的电外科手术相比得到减少。
在电外科发生器中的热离子反馈提供几个优点,包括实现组织切除和切割速率的增加,潜在的减小对附近组织的破坏以及附近烧焦的形成,以及减小神经刺激。
利用在电极处电弧的存在中出现的热离子效应作为反馈机制的激励,如本说明书所述,这使得电外科手术可以在相对较高功率密度中执行,而不造成电极损坏。因此,利用象铂这样的高熔点材料,可以实现非常高的组织切割和组织切除功率密度,或者对于给定的功率密度,相对较低成本,可以安全地使用低熔点金属或合金(例如,不锈钢)。所述系统可以用于减小电极误用和造成电极损坏的可能性。保持较大电弧减小了有源电极与组织相接触的可能性,因此降低神经刺激的可能性。
尽管本发明的选择实施例是这样一种系统,其中热离子效应是通过电外科发生器单元中的电路而感测的,即,在这一单元的外壳中可以在与发生器单元的输出端和电外科仪器之间的导电路径中耦合的附加模块中体现本发明。该模块可以具有配合到发生器单元的插座10S中的其本身的连接器,以及用于容纳在图1中所示的连接芯线14上的插头组件的插座。用于检测补偿电压的电路包含在该模块中,其连接到形成发射器单元与该仪器之间的导电路径的线路,并且电外科功率发送到该仪器是通过在该模块中的可变阻抗元件而控制的,或者通过把控制信号反馈到发送器单元的控制输入端而控制。为了避免疑问,本说明书的附加模块与分离的发生器单元的组合被认为构成在所要求的本发明的范围内的电外科发生器。
尽管所述实施例执行控制功能,即在发生器输出功率被响应所感测的热离子效应而控制或调制,但是本发明在其范围内包括一种系统,其中用于感测热离子发射的装置被简单的用作为电极温度的指示器,例如,提供用于外科医生的温度读出装置。
Claims (31)
1.一种电外科系统,包括:发生器,其包括用于把射频能量馈送到电外科仪器的治疗电极的射频源,其中该发生器包括用于感测来自该电极的热离子发射的电路。
2.根据权利要求1所述的系统,其特征在于,该发生器包括控制电路,其响应来自该感测电路的输出信号,控制馈送到治疗电极的射频能量,该感测电路和控制电路被设计为在来自该电极的热离子发射增加时减小应用的射频能量。
3.根据权利要求1或2所述的系统,其特征在于,该感测电路具有输入级,其被设计为基本上除去在工作频率或发生器频率的射频信号,以产生发生器的射频输出的平均值,并且具有耦合到该输入级来接收平均表示的检测级。
4.根据上述任何一项权利要求所述的系统,其特征在于,该发生器具有用于连接到治疗电极的输出端,并且其中该感测电路被设计为检测在高于2伏的预定电压范围内的输出端的直流电压。
5.根据权利要求4所述的系统,其特征在于,该感测电路被设计为当检测直流电压超过预定阈值时产生阈值信号。
6.根据权利要求5所述的系统,其特征在于,该阈值是在10V到100V的范围内。
7.根据权利要求3所述的系统,其特征在于,该发生器被设计为产生用于馈送到电外科仪器的治疗电极的调制射频输出,并且该感测电路被设计为基本上除去在发生器工作频率的射频信号,导致平均信号被馈送到检测级,其产生感测电路信号作为平均信号的幅度的测量值。
8.根据权利要求7所述的系统,其特征在于,感测电路输入级包括一具有通频带的滤波器,该通频带包括调制的频率但是不包括发生器的工作频率,该平均信号是一个交流信号,其频率等于调制频率。
9.根据权利要求8所述的系统,其特征在于,该发生器具有一输出级,其具有一对连接到各个发生器输出端的输出线,每条输出线具有串联隔离电容器,以及在各个隔离电容器与输出端之间的一条输出线中具有串联电感,该电感连接到感测电路的输入级。
10.根据权利要求9所述的系统,其特征在于,该输入级包括调到该调制频率并具有电感性耦合到所述串联电感的一个电感的并联谐振电路,其中该检测电路耦合到该谐振电路两端,以检测在谐振电路两端的信号幅度。
11.一种电外科系统,包括射频(r.f.)能量源,并且连接到该发生器,一个电外科仪器具有治疗电极,其中该系统包括:直流电压检测器,其被设计为检测在治疗电极上超过2伏的直流补偿,并且耦合到该检测器;控制电路,用于响应直流补偿控制施加到该仪器的射频能量。
12.根据权利要求11所述的系统,其特征在于,控制电路和检测器把直流补偿限制为预定直流电压电平。
13.根据权利要求11所述的系统,其特征在于,控制电路和检测器把直流补偿限制为在从50V到100V的范围中的一个预定值。
14.根据权利要求11至13所述的系统,其特征在于,发生器具有可连接到治疗电极的输出端,并且该检测器具有耦合到该输出端的检测输入端,以及把检测器连接到控制电路的隔离设备。
15.根据权利要求14所述的系统,其特征在于,该检测器是由发生器射频输出能量供能的,其中包括耦合到所述输出端的电源电路,并且包括用于整流施加到该输出端的射频电外科信号的整流器。
16.根据权利要求14或15所述的系统,其特征在于,该检测器包括用于产生表示直流补偿的交流测量信号的振荡器,其中该隔离设备包括光隔离器,其耦合到接收该交流测量并且把其馈送到控制电路。
17.根据权利要求11至16所述的系统,其特征在于,该检测器包括反向直流补偿检测电路,其允许(a)大于预定电压值的正直流补偿,以及(b)负直流补偿。
18.根据权利要求14至16所述的系统,其特征在于,该检测器具有耦合到发生器输出端的输入电路,该输入电路包括一个射频扼流圈以及至少2M次的串联电阻。
19.一种电外科发生器,包括:射频(r.f.)能量电源、有源输出端、返回输出端、在该电源与有源输出端之间的直流隔离电容器、具有连接在隔离电容器的输出端一侧的旁路输入端用于检测超过2伏的直流补偿电压的直流补偿检测器、以及耦合到该电源的控制电路,用于响应在所述旁路输入端的直流补偿电压控制施加到有源输出端的射频能量。
20.根据权利要求19所述的发生器,其特征在于,该控制电路和检测器把直流补偿限制为直流电压电平。
21.根据权利要求20所述的发生器,其特征在于,其把直流补偿限制为从50V到100V的范围中的预定值。
22.根据权利要求19至21中的任何一项所述的发生器,其特征在于,该检测器具有把检测器连接到控制电路的隔离设备。
23.根据权利要求22所述的发生器,其特征在于,该检测器包括连接在所述有源端和返回端之间的电源电路,并且包括用于整流施加到输出端的电外科信号的整流器。
24.根据权利要求22或23所述的发生器,其特征在于,该检测器包括用于产生表示直流补偿的交流测量信号的振荡器,并且该振荡设备包括光隔离器,其耦合到接收交流测量,并且把其馈送到控制电路。
25.根据权利要求19至24中的任何一项所述的发生器,其特征在于,该检测器包括反向直流补偿检测电路,其可以在有源输出端上检测(a)比预定电压值大的正直流补偿,和(b)负直流补偿。
26.根据权利要求22至24中的任何一项所述的发生器,其特征在于,该检测器具有耦合到发生器输出端的输入电路,该输入电路包括射频扼流圈以及至少2M次腔串联电阻。
27.一种执行电外科生物组织切割或切除的方法,其中射频(r.f.)能量被施加到电外科仪器,以便于在该仪器的治疗电极激励电弧,这种能量的电平被根据从该电极发射的热离子的电平而调节。
28.根据权利要求27所述的方法,其特征在于,该射频能量被调节为使电极的温度最大化,而基本上不产生电极燃烧。
29.根据权利要求27所述的方法,其特征在于,该射频能量被调节为该直流电源限制为小于100V的阈值。
30.一种电外科发生器,包括可以在发生器工作频率工作的射频(r.f.)电源以及包括一对射频能量输出端的输出级,该输出级与该电源直流隔离,该发生器还包括用于调制由该电源所产生的射频功率信号的装置,以及与该输出级交流耦合并直流隔离的感测电路,其可产生包含表示在传送到输出端的功率信号中的直流漂移的调制成分的平均直流信号。
31.根据权利要求30所述的发生器,其特征在于,该调制装置在预定调制频率产生射频功率信号中的幅度调制,并且发生器还包括与感测电路相关联的滤波元件,用于基本上从感测电路的输入中在工作频率上除去射频分量,以产生平均交流信号。
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DE1099658B (de) * | 1959-04-29 | 1961-02-16 | Siemens Reiniger Werke Ag | Selbsttaetige Einschaltvorrichtung fuer Hochfrequenzchirurgiegeraete |
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DE2801833C2 (de) * | 1978-01-17 | 1979-11-29 | Aesculap-Werke Ag Vormals Jetter & Scheerer, 7200 Tuttlingen | Elektrochirurgische Schneidvorrichtung |
DE3911416A1 (de) * | 1989-04-07 | 1990-10-11 | Delma Elektro Med App | Elektrochirurgisches hochfrequenzgeraet |
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- 1999-05-21 GB GBGB9911954.7A patent/GB9911954D0/en not_active Ceased
-
2000
- 2000-05-18 EP EP00304211A patent/EP1053719A1/en not_active Withdrawn
- 2000-05-19 AU AU35406/00A patent/AU3540600A/en not_active Abandoned
- 2000-05-19 CA CA 2308879 patent/CA2308879A1/en not_active Abandoned
- 2000-05-19 BR BR0013450-3A patent/BR0013450A/pt not_active Application Discontinuation
- 2000-05-19 JP JP2000147958A patent/JP2000350732A/ja not_active Withdrawn
- 2000-05-22 CN CN 00107594 patent/CN1274566A/zh active Pending
Cited By (11)
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CN100457059C (zh) * | 2005-07-12 | 2009-02-04 | 付洁宇 | 多路射频消融治疗仪 |
CN101404948B (zh) * | 2006-03-22 | 2012-02-29 | 奥林巴斯医疗株式会社 | 医疗设备 |
CN101736315B (zh) * | 2008-11-27 | 2011-12-07 | 中芯国际集成电路制造(上海)有限公司 | 射频发生器的离线检测装置 |
CN102971939A (zh) * | 2010-03-30 | 2013-03-13 | 丰田自动车株式会社 | 电压检测器、异常检测装置、非接触输电装置、非接触受电装置以及车辆 |
US8907680B2 (en) | 2010-03-30 | 2014-12-09 | Nippon Soken, Inc. | Voltage detector, malfunction detecting device, contactless power transmitting device, contactless power receiving device, and vehicle |
CN102971939B (zh) * | 2010-03-30 | 2015-11-25 | 丰田自动车株式会社 | 电压检测器、异常检测装置、非接触输电装置、非接触受电装置以及车辆 |
CN108389893A (zh) * | 2011-12-01 | 2018-08-10 | 伊利诺伊大学评议会 | 经设计以经历可编程转变的瞬态器件 |
CN104125810A (zh) * | 2012-06-15 | 2014-10-29 | 奥林巴斯医疗株式会社 | 处置系统 |
CN107847265A (zh) * | 2015-07-22 | 2018-03-27 | 欧泰克工业有限公司 | 用于对人或动物患者的身体进行组织切割的电外科装置 |
CN107847265B (zh) * | 2015-07-22 | 2021-11-26 | 欧泰克工业有限公司 | 用于对人或动物患者的身体进行组织切割的电外科装置 |
CN105266892A (zh) * | 2015-10-16 | 2016-01-27 | 中国人民解放军第四军医大学 | 一种双极电凝器调控装置 |
Also Published As
Publication number | Publication date |
---|---|
GB9911954D0 (en) | 1999-07-21 |
CA2308879A1 (en) | 2000-11-21 |
JP2000350732A (ja) | 2000-12-19 |
AU3540600A (en) | 2000-11-23 |
BR0013450A (pt) | 2002-04-23 |
EP1053719A1 (en) | 2000-11-22 |
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