CN105992563B - 医疗装置 - Google Patents

医疗装置 Download PDF

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CN105992563B
CN105992563B CN201480075553.1A CN201480075553A CN105992563B CN 105992563 B CN105992563 B CN 105992563B CN 201480075553 A CN201480075553 A CN 201480075553A CN 105992563 B CN105992563 B CN 105992563B
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A·E·格林
P·C·罗伯茨
M·D·图克威尔
P·R·博罕姆
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Isikang Medical Surgery Co ltd
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Abstract

本发明描述了一种医疗装置，所述医疗装置具有柄部、联接至所述柄部的轴和联接至所述轴的端部执行器。在一个实施方案中，所述装置包括超声换能器且被布置成使得超声能量或电能可传送至待治疗的血管或组织。本发明描述了各种新颖的感测电路以使得能够测量驱动信号的量度并将其反馈回至控制器。本发明还描述了主动熔丝电路，所述主动熔丝电路用于保护所述装置的一个或多个电池免于过流情况。

Description

医疗装置
本发明涉及医疗装置领域，且具体地讲涉及但并非仅涉及医疗烧灼和切割装置。本发明还涉及用于驱动此类医疗装置的驱动电路和方法。
许多外科手术需要切割或结扎血管或其它内部组织且许多手术是通过用于进行切割或结扎的手持式烧灼装置使用微创技术来进行。一些现有的手持式烧灼装置使用烧灼装置中的超声换能器来向待切割或结扎的组织施加超声能量。其它手持式烧灼装置通过所述装置的夹钳直接向被烧灼的组织/血管施加射频能量。
本发明旨在提供一种能够向待烧灼的血管或组织施加超声能量或射频能量的替代外科装置。本发明的其它方面涉及提供控制电路以在不同的操作模式之间进行选择的方式。本发明的其它方面涉及可在电路设计中进行电压和电流测量以向诸如微处理器等控制器报告的方式；和可提供控制电路以确保不会从电池消耗太多电流的方式。
根据一个方面，本发明提供一种医疗装置，所述医疗装置包括：端部执行器，用于夹持血管/组织；超声换能器，联接至所述端部执行器；驱动电路，联接至所述端部执行器并且联接至所述超声换能器且能够操作以产生周期性驱动信号并将所述驱动信号提供至所述超声换能器或提供至所述端部执行器；和控制器，能够操作以控制所述驱动电路，使得所述驱动信号施加到所述超声换能器和所述端部执行器中的期望的一者。
在一个实施方案中，所述驱动电路包括具有第一谐振频率的第一谐振电路和具有不同于所述第一谐振频率的第二谐振频率的第二谐振电路，其中所述第一谐振频率对应于所述超声换能器的谐振特性，并且其中所述控制器能够操作以控制所述驱动电路，使得当驱动信号待施加到所述超声换能器上时，所述驱动电路产生具有对应于所述第一谐振频率的频率的驱动信号，并且使得当驱动信号待施加到所述端部执行器上时，所述驱动电路产生具有对应于所述第二谐振频率的频率的驱动信号。
还可提供信号发生器，所述信号发生器联接在所述控制器与所述驱动电路之间，用于依据来自所述控制器的控制信号从直流电压源产生周期性变化的电压并且用于将所述周期性变化的电压供应至所述驱动电路的所述第一谐振电路和所述第二谐振电路。
所述控制器可被布置成围绕所述第一谐振频率或所述第二谐振频率改变所述驱动信号的周期，以改变供应至被所述端部执行器夹持的所述血管或组织的能量。所述控制器可改变所述驱动信号的周期，使得所述驱动信号的频率围绕所述第一谐振频率在所述第一谐振频率的0.1％至1％的范围内变化；或者使得所述驱动信号的频率围绕所述第二谐振频率在所述第二谐振频率的40％至60％的范围内变化。
通常，所述第一谐振电路和所述第二谐振电路的谐振特性随被所述夹钳夹持的所述组织或血管而变化且在一个实施方案中，所述控制器被构造成能够改变所述驱动信号的所述周期以跟踪相应谐振特性的变化。
可提供超声波导，所述超声波导联接至所述超声换能器，用于将由所述超声换能器产生的超声能量朝向所述端部执行器引导。所述端部执行器可包括第一钳口和第二钳口且所述第二谐振电路可电联接至所述端部执行器的所述第一钳口和所述第二钳口。例如，所述端部执行器的所述第一钳口可电联接至所述波导且所述第二谐振电路可通过所述超声波导电联接至所述端部执行器的所述第一钳口。在一些实施方案中，所述第一谐振电路电联接至所述超声换能器并且电联接至所述波导。
可提供感测电路以感测施加到所述超声换能器或施加到所述端部执行器上的驱动信号。在一个实施方案中，所述第一谐振电路和所述第二谐振电路中的一者或两者可包括电感器线圈、电容器和电阻器中的至少一者，且其中所述感测电路可包括运算放大器电路，所述运算放大器电路用于感测所述电感器线圈或所述电容器或所述电阻器上的电压并且用于将所述感测到的电压转换成适于输入到所述控制器的传感器信号。在另选的实施方案中，所述第一谐振电路和所述第二谐振电路中的一者或两者可包括连接在所述谐振电路与参考电位之间的阻抗元件，且其中所述感测电路包括分配器电路和偏压信号发生器，所述分配器电路用于获得所述阻抗元件上的所述电压的量度，所述偏压信号发生器用于向所述电压量度施加直流偏压信号。在这种情况下，所述阻抗元件可包括电容器或电阻器。通常，所述感测电路包括用于防止来自所述偏压信号发生器的所述直流偏压信号与所述驱动电路联接的直流阻塞电路。所述偏压信号发生器可包括分配器电路，所述分配器电路连接在基准电压与所述控制器的电源电压之间。
所述装置优选地为电池驱动装置且包括用于对所述装置提供功率的一个或多个电池，并且还包括用于保护所述一个或多个电池的主动熔丝电路。所述主动熔丝电路可包括开关和控制电路，所述开关电联接在所述一个或多个电池的端子与所述驱动电路之间，所述控制电路被构造成能够断开所述开关以使所述电源端子与所述驱动电路隔离。
本发明还提供一种医疗装置，所述医疗装置包括：端部执行器，用于夹持血管/组织；驱动电路，用于产生周期性变化的驱动信号以将能量驱动到所述血管/组织中；感测电路，用于感测由所述驱动电路产生的驱动信号；和控制器，响应于所述感测电路并且能够操作以控制所述驱动电路来控制传送至所述血管/组织的所述能量；其中所述驱动电路包括联接至参考电位的阻抗元件，且其中所述感测电路包括分配器电路和偏压信号发生器，所述分配器电路用于获得所述阻抗元件上的所述电压的量度，所述偏压信号发生器用于向所述电压量度施加直流偏压信号。
所述阻抗元件可为电容器或电阻器。所述感测电路还可包括用于防止来自所述偏压信号发生器的所述直流偏压信号与所述驱动电路联接的直流阻塞电路。所述偏压信号发生器可包括分配器电路，所述分配器电路连接在基准电压与所述控制器的电源电压之间。所述偏压信号发生器的所述分配器电路可通过开关连接至所述控制器的所述电源电压，且其中所述控制器被构造成能够在所述控制器不需要来自所述感测电路的信号时断开所述开关。
本发明还提供一种医疗装置，所述医疗装置包括：端部执行器，用于夹持血管/组织；一个或多个电池，用于提供直流电压电源；信号发生器，联接至所述一个或多个电池，用于从所述直流电压电源产生周期性变化的驱动信号，以将能量驱动到所述血管/组织中；控制器，能够操作以控制所述信号发生器来控制传送至所述血管/组织的所述能量；和主动熔丝电路，联接在所述一个或多个电池与所述信号发生器之间，用于保护所述一个或多个电池。
所述主动熔丝电路可包括：开关，其电联接在所述一个或多个电池的端子与所述信号发生器之间；和控制电路，其被构造成能够切换所述开关。所述开关可被布置成将所述信号发生器与所述一个或多个电池断开或者可连接所述信号发生器与所述一个或多个电池之间的大阻抗。
所述主动熔丝的所述控制电路可包括用于感测从所述一个或多个电池消耗的所述电流的量度并且被构造成能够在所述电流量度超过阈值的情况下切换所述开关的电路。所述主动熔丝的所述控制电路可包括用于比较所述电流量度与所述阈值的比较器，且其中所述比较器的输出控制所述开关的断开和闭合。
本发明还提供一种操作医疗装置的方法，所述方法包括产生周期性驱动信号并将所述驱动信号施加到所述医疗装置的超声换能器或施加到所述医疗装置的端部执行器，并且控制所述驱动电路，使得所述驱动信号施加到所述超声换能器和所述端部执行器中的期望一者。
本发明还提供一种烧灼或切割血管或组织的方法，所述方法包括：用医疗装置的端部执行器来夹持所述血管或组织；使用驱动电路来向超声换能器或向所述端部执行器施加周期性驱动信号；和控制所述驱动电路，使得所述驱动信号施加到所述超声换能器和所述端部执行器中的期望一者。所述方法可使用上述医疗装置。
本发明还提供一种用于具有超声换能器和端部执行器的医疗装置的电子设备，所述电子设备包括：驱动电路，用于产生周期性驱动信号；和控制器，能够操作以控制所述驱动电路，使得所述驱动信号施加到所述超声换能器和所述端部执行器中的期望的一者；其中所述驱动电路包括具有第一谐振频率的第一谐振电路和具有不同于所述第一谐振频率的第二谐振频率的第二谐振电路，并且其中所述控制器能够操作以控制所述驱动电路，使得当驱动信号待施加到所述超声换能器上时，所述驱动电路产生具有对应于所述第一谐振频率的频率的驱动信号，并且使得当驱动信号待施加到所述端部执行器上时，所述驱动电路产生具有对应于所述第二谐振频率的频率的驱动信号。
本发明还提供一种医疗装置，所述医疗装置包括：端部执行器，用于夹持血管/组织；驱动电路，联接至所述端部执行器并且能够操作以产生驱动信号并将所述驱动信号提供至所述端部执行器；控制器，能够操作以产生控制信号并将其输出到所述驱动电路以控制由所述驱动电路产生的所述驱动信号；其中所述驱动电路和由被所述端部执行器夹持的所述血管/组织形成的负载限定谐振电路，该谐振电路的谐振频率随着由被所述端部执行器夹持的所述血管/组织形成的所述负载的阻抗的变化而变化；其中所述控制器被布置成产生控制信号，所述控制信号致使所述驱动电路产生驱动信号，所述驱动信号具有在所述谐振频率变化时跟踪所述谐振频率的频率；并且其中所述控制器还被布置成减少传送至由被所述端部执行器夹持的所述血管/组织形成的所述负载的功率、电流或电压中的一者或多者。
可提供传感器电路和测量电路，所述传感器电路用于感测施加到由被所述端部执行器夹持的所述血管/组织形成的所述负载的信号，所述测量电路用于处理来自所述传感器电路的所述信号，以确定由被所述端部执行器夹持的所述血管/组织形成的所述负载的所述阻抗的量度。在这种情况下，所述控制器可依据由被所述端部执行器夹持的所述血管/组织形成的所述负载的所述阻抗的所述量度来产生所述控制信号。
在一个实施方案中，所述控制器产生具有脉冲序列的控制信号且所述控制器跳过来自所述控制信号的一个或多个脉冲，以便减少传送至由被所述端部执行器夹持的所述血管/组织形成的所述负载的功率、电流或电压中的一者或多者。
通常，在这种情况下，所述控制器包括以依从于所述谐振频率的期望的频率产生脉冲的脉冲信号发生器且所述控制器通过抑制由所述脉冲信号发生器产生的脉冲而跳过由所述脉冲信号发生器产生的脉冲。
通过参照附图描述的实施方案的下述详细说明，本发明的这些和各种其它特征结构和方面将变得显而易见，其中：
图1示出手持式烧灼装置，在所述装置的柄部部分中安装有电池以及驱动和控制电路；
图2为示出在本发明的一个实施方案中使用的烧灼装置的主要部件的部分方框图；
图3为示出图2所示烧灼装置的主要电部件的电路图；
图4示意性地示出超声换能器联接至波导以将所产生的超声能量传送至夹钳的方式并且示出图3所示电路可向夹钳传送电能的方式；
图5为示意性地示出形成图2所示微处理器的一部分的处理模块的方框图；
图6示出由微处理器产生以控制驱动电路同时使3次谐波含量最小化的控制信号的形式；
图7为示出传送功率对负载电阻和驱动频率的关系曲线的轮廓曲线图；
图8a为示出可确定负载电流的量度并将其供应至微处理器的一种方式的电路图；
图8b为示出可确定负载电流的量度并将其供应至微处理器的另一种方式的电路图；
图8c为示出可确定负载电压的量度并将其供应至微处理器的一种方式的电路图；
图9a为示出可确定负载电流的量度并将负载电流的量度供应至微处理器而不使用运算放大器的一种方式的电路图；
图9b为示出可确定负载电流的量度并将负载电流的量度供应至微处理器的一种方式且示出可确定负载电压的量度并将其供应至微处理器而不使用运算放大器的一种方式的电路图；和
图10为示出用于保护图2所示电池免于过量电流需求的主动熔丝电路的电路图。
医疗装置
许多外科手术需要对血管或其它血管组织进行切割或结扎。外科医生通过患者体内的小切口执行微创外科手术。由于空间有限，因此外科医生通常难以通过夹紧和/或捆扎横断的血管来控制流血。通过利用超声外科夹钳或电外科夹钳，外科医生可通过下述方式来烧灼、凝聚/脱水、和/或仅减少出血：控制由超声换能器施加到组织/血管的超声能量或控制通过夹钳施加到组织/血管的射频能量。
图1示出根据本发明的一个实施方案的被设计用于微创医疗手术的超声/射频外科医疗装置1的形式。如图所示，装置1是具有细长轴3的自含式装置，此细长轴具有连接至轴3的近端的手柄5和连接至轴3的远端的端部执行器7。在本实施方案中，端部执行器7包括由操纵柄部5的控制杆11和13的用户控制的医疗夹钳9。
在外科手术期间，轴3穿过套管针插入以进入患者体内和手术部位。外科医生将使用柄部5以及控制杆11和13来操纵夹钳9，直至夹钳9位于待切割或烧灼的组织周围。电能随后直接通过夹钳9以受控方式施加到组织(作为射频能量)或通过轴3内的波导(未示出)施加到安装在柄部5内并且联接至夹钳9的超声换能器8，以便使用超声能量来进行所期望的切割/烧灼。如图1所示，在本实施方案中，柄部5还容纳用于产生和控制进行烧灼所需的电能的电池15和控制电子器件17。以这种方式，就装置无需单独的控制盒和电源线以向夹钳9提供电能的意义而言，装置1是自含式的。然而，如果需要，则可提供这种单独的控制盒。
系统电路
图2为在本实施方案中用来产生和控制供应至超声换能器或供应至夹钳9的电能的烧灼/切割装置1的主要电路的示意性方框图。如下文将更详细地解释，在本实施方案中，所述电路被设计成控制产生以便控制传送至被烧灼的组织/血管的功率的量的电驱动波形的周期。
如图2所示，烧灼/切割装置1包括用户界面21-通过用户界面21来向用户提供信息(例如正通过电能或超声能量向被夹持的组织/血管施加能量的指示)且用户通过用户界面21来控制烧灼/切割装置1的操作，包括对超声操作或射频操作的选择。如图所示，用户界面21联接至微处理器23，微处理器23通过产生由其输出到栅极驱动电路25的控制信号来控制切割/烧灼手术。响应于来自微处理器23的控制信号，栅极驱动电路25产生栅极控制信号，所述栅极控制信号致使桥信号发生器27产生通过驱动电路29施加到超声换能器8或施加到夹钳9的期望的驱动波形。电压感测电路31和电流感测电路33产生施加到超声换能器8或施加到夹钳9的电流和电压的量度，电压感测电路31和电流感测电路33将所述量度反馈回至微处理器23以用于控制目的。图2还示出提供用于对图2所示电路提供功率的功率的电池15。在本实施方案中，电池15被布置成供应OV轨和14V轨。
图3更详细地示出栅极驱动电路25、桥信号发生器27和驱动电路29的部件。图3还示出压电超声换能器8和由待治疗的组织/血管形成的负载(R负载)的电等效电路30。如图3所示，栅极驱动电路25包括两个FET栅极驱动器37-FET栅极驱动器37-1和FET栅极驱动器37-2。来自微处理器23的第一组控制信号(CTRL1)供应至FET栅极驱动器37-1且来自微处理器23的第二组控制信号(CTRL2)供应至FET栅极驱动器37-2。FET栅极驱动器37-1使用第一组控制信号(CTRL1)来产生两个驱动信号－一个用于驱动桥信号发生器27的所述两个FET41-1和41-2中的每一者。FET栅极驱动器37-1产生驱动信号，所述信号致使上部FET(41-1)在下部FET(41-2)关断时接通，反之亦然。这致使节点A交替地连接至14V轨(当FET41-1接通时)和OV轨(当FET 41-2接通时)。相似地，FET栅极驱动器37-2使用第二组控制信号(CTRL2)来产生两个驱动信号－一个用于驱动桥信号发生器器27的所述两个FET 41-3和41-4中的每一者。FET栅极驱动器37-2产生驱动信号，所述驱动信号致使上部FET(41-3)在下部FET(41-4)关断时接通，反之亦然。这致使节点B交替地连接至14V轨(当FET41-3接通时)和0V轨(当FET 41-4接通时)。因此，由微处理器23输出的所述两组控制信号(CTRL1和CTRL2)控制产生且施加在节点A与节点B之间的数字波形。每组控制信号(CTRL1和CTRL2)由一对信号线组成，一个用于指示高侧FET何时接通且另一个用于指示低侧FET何时接通。因此，微处理器23通过软件或通过专用硬件功能可确保不会发生当高侧FET和低侧FET同时接通时的不期望的条件。实际上，这需要在高侧FET和低侧FET关断时留下空载时间以确保，甚至当允许可变切换延迟时，也不会存在所述两个FET可同时接通的可能性。在本实施方案中，使用了约100ns的空载时间。
如图3所示，节点A和节点B连接至驱动电路29，因此由桥信号发生器27产生的数字电压施加到驱动电路29。此施加电压将致使电流在驱动电路29中流动。如图3所示，驱动电路29包括两个变压器电路42-1和42-2。第一变压器电路42-1被设计用于超声换能器8的高效驱动且包括由电容器CUS s 45、电感器LUS s 47和电感器LUS m 49形成的电容器-电感器-电感器谐振电路43-1。当驱动超声换能器8时，微处理器23被布置成产生栅极驱动电路25的控制信号，使得在节点A和节点B两端施加的数字电压的基本频率(fd)为大约谐振电路43-1的谐振频率，谐振电路43-1的谐振频率在本实施方案中为约50kHz。由于谐振电路43-1的谐振特性，在节点A和节点B两端施加的数字电压将致使处于基本频率(fd)下的基本上正弦电流在谐振电路43-1内流动。这是因为将通过谐振电路43-1以及称为变压器初级的Lt和Ct1的阻抗对驱动电压的更高次谐波含量进行衰减。
如图3所示，电感器LUS m 49形成变压器电路42-1的初级，其次级由电感器LUS sec 53形成。变压器将电感器Lm 49两端的驱动电压(VUS d)上转换为施加到超声换能器8的负载电压(VL；通常为约120伏)。超声换能器8的电特性随夹钳的钳口和被夹钳9夹持的任何组织或血管的阻抗而变化；且图3通过电感器Lt 57、并联电容器Ct1 59和Ct2 61以及电阻R负载来模型化超声换能器8以及夹钳的钳口和被夹钳9夹持的任何组织或血管的阻抗。
驱动电路29的电感器LUS s和电容器CUS s被设计成具有与超声换能器8的电感器Lt和电容器Ct1的LC乘积相匹配的LC乘积。匹配串联LC网络的LC乘积确保网络的谐振频率得以保持。相似地，电感器LUS m的磁抗被选择成使得在谐振下电感器LUS m的磁抗与超声换能器8的电容器Ct2的容抗相匹配。例如，如果换能器8被限定成使得电容器Ct2具有约3.3nF的电容，则电感器LUS m应具有约3mH的电感(在约50kHz的谐振频率下)。以这种方式设计驱动电路29提供就至被夹钳9夹持的组织/血管的能量传送而言最佳的驱动效率。实现效率改善，因为在CUS s且因此FET桥27中流动的电流减少，因为变压器磁化电流消除在Ct2中流动的电流。此外，由于此电流消除，在CUS s中流动的电流与在R负载中流动的电流成比例，从而允许通过测量在CUS s中流动的电流来确定负载电流。
第二变压器电路42-2被设计用于电射频能量通过夹钳9直接向组织/血管的高效驱动且包括由电容器CF s 46、电感器LF s 48和电感器LF m 50形成的电容器-电感器-电感器谐振电路43-2。当直接通过电能来驱动夹钳9时，微处理器23被布置成产生栅极驱动电路25的控制信号，使得在节点A和节点B两端施加的数字电压的基本频率(fd)为大约谐振电路43-2的谐振频率，谐振电路43-2的谐振频率在本实施方案中为约500kHz。由于谐振电路43-2的谐振特性，在节点A和节点B两端施加的数字电压将致使处于基本频率(fd)下的基本上正弦电流在谐振电路43-2内流动。这是因为将通过谐振电路43-2对驱动电压的更高次谐波含量进行衰减。
如图3所示，电感器LF m 50形成变压器电路42-1的初级，其次级由电感器LUS sec 54形成。变压器将电感器LF m 50两端的驱动电压(VF d)上转换为施加到夹钳9的负载电压(VF L；通常为约120伏)。被夹钳9的钳口夹持的组织或血管表示为在图3中标记为9的盒中的电阻负载R负载。实际上，这将是超声换能器8的电等效电路30中所示的相同的电阻负载。
图4为示出超声换能器8联接至待烧灼的组织/血管的方式和图3所示电路部件连接至超声换能器8并连接至夹钳9的方式的示意图。具体地讲，图4示出轴3、夹钳9和超声换能器8。图4还示出波导72，沿着波导72引导由超声换能器8产生的超声信号。波导72连接至图3所示节点“BB”，而至超声换能器8的输入电源连接至图3所示节点“AA”。第二变压器电路42-2的输出节点“CC”连接至护套3的导电内壁，护套3电连接至夹钳9的上钳口74。返回路径穿过待烧灼的组织/血管和下钳口76，下钳口76电连接至节点“BB”。
当驱动信号具有约50kHz的驱动频率时，几乎没有电流将在第二变压器电路42-2内流动，因为驱动频率远离谐振电路43-2的谐振频率，使得第二变压器电路42-2的输入阻抗对于此驱动信号而言将是非常高的。因此，功率将几乎完全通过第一变压器电路42-1传送。相似地，当驱动信号具有约500kHz的驱动频率时，几乎没有电流将在第一变压器电路42-1内流动，因为驱动频率远离谐振电路43-1的谐振频率，使得第一变压器电路42-1的输入阻抗对于此驱动信号而言将是非常高的。因此，功率将几乎完全通过第二变压器电路42-2传送。以这种方式，所述两个变压器电路42-1和42-2可由共同的桥信号发生器器27驱动；尽管以单独的桥信号发生器器来驱动每个变压器电路也是可行的。
并不总是期望向待治疗的组织/血管施加全功率。因此，在本实施方案中，在超声操作模式下，通过改变在节点A和节点B两端施加的数字波形的周期来控制供应至血管/组织的超声能量的量，使得驱动频率(fd)移动远离超声换能器8的谐振频率。这起作用，因为超声换能器8充当频率依从(无损)衰减器。驱动信号越靠近超声换能器8的谐振频率，超声换能器8将产生越多的超声能量。相似地，当驱动信号的频率移动远离超声换能器8的谐振频率时，超声换能器8就会产生越来越少的超声能量。除此之外或作为另外一种选择，可改变驱动信号的脉冲的持续时间以控制传送至组织/血管的超声能量的量。
相似地，在电操作模式下，通过改变在节点A和节点B两端施加的数字波形的周期来控制供应至夹钳9的电功率的量，使得驱动频率(fd)移动远离谐振电路43-2的谐振频率。这起作用，因为谐振电路43-1充当频率依从(无损)衰减器。驱动信号越靠近谐振电路43-1的谐振频率，驱动信号衰减得就越少。相反，当驱动信号的频率移动远离电路43-1的谐振频率时，驱动信号衰减更多且因此供应至组织/血管的电能减少。驱动频率需要移动远离谐振频率达谐振频率的约50％以实现所期望的功率变化范围。控制在电操作模式期间施加的功率、电流或电压的另选方法是连续地调谐激发信号的频率以使它保持与驱动电路的谐振频率相匹配(在它随变化的负载阻抗而变化时)，从而保持高效操作并且跳过驱动控制信号的脉冲中的一些，直至平均功率、电流和/或电压低于相关限制。
当使用脉冲跳跃技术时最有效的另一替代方案是移除图3所示的电感器48且因此用于电操作模式的驱动电路变为基本上并联LC谐振电路(它不是纯并联LC谐振电路，因为变压器漏电感似乎与电感器48串联且无法被完全移除)。移除电感器48的优点在于可提高总效率，因为再也不存在电感器的任何损失。另一优点在于可减小电路的物理尺寸，因为常常电感器相对于FET、微处理器、电容器和其它系统部件为身体大的部件。
微处理器23基于如下来控制功率传送：待传送至电路30(其模型化超声换能器8和被夹钳9夹持的组织/血管)或传送至夹钳9的期望的功率以及从电压感测电路31和电流感测电路33获得的负载电压(VL)和负载电流(iL)的测量。微处理器23还基于通过选择电操作或超声操作的用户界面21接收到的用户输入来选择驱动信号的频率(大约50kHz或大约500kHz)。
微处理器
图5为示出在本实施方案中使用的微处理器23的主要部件的方框图。如图所示，微处理器23包括同步I、Q采样电路81，所述电路从感测电路31和33接收感测电压和电流信号并且获得对应样品，所述样品被传递至测定电压和电流处理模块83。测定电压和电流处理模块83使用所接收到的样品来计算施加到超声换能器8和/或直接施加到被夹钳9夹持的组织/血管的RMS电压和流动穿过超声换能器8和/或直接流动至被夹钳9夹持的组织/血管的RMS电流的阻抗；并且从其计算当前供应至电路30或直接供应至被夹钳9夹持的组织/血管的功率。所确定的值然后被传递至功率控制器85以供进一步处理。测定电压和电流处理模块83还可处理所接收到的I样品和Q样品以计算负载电压(VL)与负载电流(iL)之间的相位差。在超声操作模式期间，在谐振下，此相位差应为大约零且因此此相位量度可用作功率控制器85的反馈参数。
功率控制器85使用所接收到的阻抗值和传送功率值以根据预定算法以及功率设定点值和模式指示信号(从医疗装置控制模块89接收且指示超声操作或电操作)来确定用于控制栅极驱动电路25的控制信号(CTRL1和CTRL2)的期望的周期/频率(Δt新)。此期望的周期/频率从功率控制器85传递至控制信号发生器95，控制信号发生器95改变控制信号CTRL1和CTRL2，以便将波形周期改变为与所期望的周期相匹配。CTRL控制信号可包括具有期望的周期的方波信号或它们可包括周期脉冲，其中所述周期脉冲具有对应期望的周期(Δt新)，且其中所述控制信号的脉冲的相对定时被设定成使由桥信号发生器27产生的波形的谐波含量最小化(例如使3阶谐波最小化)。在本实施方案中，控制信号CTRL1输出到FET栅极驱动器37-1(示于图2中)，FET栅极驱动器37-1放大控制信号，然后将它们施加到FET 41-1和41-2；且控制信号CTRL2输出到FET栅极驱动器37-2(示于图2中)，FET栅极驱动器37-2放大控制信号，然后将它们施加到FET 41-3和41-4，从而产生具有新的周期(Δt新)的期望的波形。
为了以最佳的RMS波形来驱动电路，MOSFET 41作为互补、相对的对驱动。尽管当以180度的相移驱动MOSFET时实现最大输出电压，但这种驱动波形的所得谐波含量，特别是3次谐波(其被输出滤波器不佳地排除)相当高。本发明人已发现，对于减少3次谐波，施加到所述两对MOSFET41的控制信号之间的最佳相移为大约120°。这示于图6中，图6示出在上部曲线中来自第一MOSFET对41-1和41-2的输出；在中间曲线中来自第二MOSFET对41-3和41-4的输出(相对于上部曲线移位120°)；和在下部曲线中在输入A和输入B两端施加的所得(正常化)输出电压。此正常化输出电压的形状具有很低的3阶谐波含量。
I和Q信号采样
负载电压和负载电流两者均将为基本上正弦波形，但它们可根据由换能器8和/或被夹钳9夹持的血管/组织代表的负载的阻抗而不同相。负载电流和负载电压将处于对应当前限定波形周期(Δt新)的相同驱动频率(fd)下。正常地，当对信号进行采样时，采样电路相对于正被采样的信号的频率以异步方式操作。然而，当微处理器23知道切换信号的频率和相位时，同步采样电路81可在驱动周期期间的预定时间点对测定电压/电流信号进行采样。在本实施方案中，在超声操作模式期间，同步采样电路81每周期八次对测定信号进行过采样，以获得四个I样品和四个Q样品。过采样允许减少由谐波失真所引起的错误且因此允许更精确确定测定电流值和电压值。然而，过采样并不是必要的且实际上欠采样(每周期少于两个样本)是在装置以电操作模式操作时进行且因采样操作的同步性质而可行。同步采样电路81制作这些样品的定时在本实施方案中由控制信号CTRL1和CTRL2控制。因此，当这些控制信号的周期被改变时，采样控制信号CTRL1和CTRL2的周期也改变(而其相对相位保持相同)。以这种方式，当驱动波形的周期被改变时，采样电路81连续地改变其对感测电压和电流信号进行采样的定时，使得所述样品始终在驱动波形的周期内的相同时间点获取。因此，采样电路81进行“同步”采样操作，而不是更常规的采样操作，即只以由固定采样钟限定的固定采样速率对输入信号进行采样。当然，也可使用这种常规的采样操作。
测量
由同步采样电路51获得的样品被传递至测定电压和电流处理模块83，测定电压和电流处理模块83可从负载电流和负载电压的仅一个“I”样品和一个“Q”样品确定测定信号的幅度和相位。然而，在本实施方案中，为实现一些平均，处理模块83对连续的“I”样品进行平均化以提供平均的“I”值并对连续的“Q”样品进行平均化以提供平均的“Q”值；然后使用平均的I值和Q值来确定测定信号的幅度和相位。当然，应当识别到，可能需要对数据进行一些预处理以将实际测定I样品和Q样品转换成负载电压或负载电流的I样品和Q样品，例如，可对样品值进行缩放、积分或微分以将所采样的值转换成负载电压(VL)和负载电流(iL)的真样品。在需要积分或微分情况下，这可仅通过交换I样品和Q样品的次序来实现－因为对正弦信号进行积分/微分仅涉及缩放和90度相移。
然后可从以下确定RMS负载电压、RMS负载电流和传送功率Pdelivered：
Figure BDA0001078613420000141
Figure BDA0001078613420000142
Figure BDA0001078613420000143
Figure BDA0001078613420000144
Figure BDA0001078613420000145
Figure BDA0001078613420000146
可从以下确定由超声换能器8和被夹钳9夹持的血管/组织代表的负载的阻抗(或在电能直接施加到夹钳9的情况下仅夹钳9或被夹钳9夹持的血管/组织的阻抗)：
Figure BDA0001078613420000151
计算R负载和X负载的另选方式如下：
Figure BDA0001078613420000152
并且可从以下确定负载电压与负载电流之间的相位差：
Phasemeasured＝atan2(Preactive,Pdelivered)
计算效率高、逼近的atan2的函数可使用查找表和定点算术中的内插，或使用类似于算法的“CORDIC”来进行。
极限值
如同任何系统一样，存在可对可传送至超声换能器8或传送至夹钳9的功率、电流和电压设置的某些极限值。现在将描述本实施方案中使用的极限值以及如何控制它们。
在本实施方案中，驱动电路29被设计成根据下述要求将超声能量传送至组织中或将电能传送至组织中：
1)供应有额定14V直流电源
2)就超声操作而言，处于大约50kHz下的基本上正弦输出波形
3)就射频电操作而言，处于大约500kHz下的基本上正弦输出波形
4)就超声操作而言，90W的功率限定输出
5)就电操作而言，100W的功率限定输出
6)就超声操作而言，限定为1.4Arms的电流和限定为130Vrms的电压
7)就电操作而言限定为1.4Arms的电流和限定为100Vrms的电压
8)就超声操作而言，测定相位大于系统定义相位极限值
功率控制器85保持定义这些极限值的数据并且使用这些数据来控制关于假定最新测定功率、负载阻抗和/或测定相位是增大还是减小波形周期或是否跳过控制信号的脉冲的决策。在本实施方案中，当以超声操作模式操作时，所使用的相位极限值依从于测定负载阻抗。具体地讲，功率控制器85保持使负载阻抗与相位极限值相关的查找表(未示出)；且此表中的值限制相位极限值，使得当测定负载阻抗为低(指示夹钳9的钳口打开且不夹持组织或血管)时，传送功率减少(优选地减少到零)。
如上所述，控制所述装置的操作的方式之一(当以电操作模式操作时)是使驱动效率最大化。当以这种方式控制所述装置时，功率控制器85跟踪当负载变化时最大功率传送条件。现在描述可做到这一点的方式。
最大功率传送跟踪条件
可通过以下方程式来粗略估计图3所示电路的复阻抗(当以电操作模式操作时且在电感器48移除时)：
Figure BDA0001078613420000161
其中：
R负载_ref为称为初级的负载电阻(乘以线匝比的平方)；且Rs代表电感器、变压器电容器和切换装置的等效串联电阻。此复阻抗可改写为：
Figure BDA0001078613420000162
因此，此复阻抗的实数部分为：
Figure BDA0001078613420000163
且此复阻抗的虚数部分为：
Figure BDA0001078613420000171
当驱动频率(f)对应此复阻抗的谐振频率时，虚数部分
Figure BDA0001078613420000172
因此，功率控制器85可使用锁相回路来改变驱动频率(f)以使虚数部分
Figure BDA0001078613420000173
保持为零或大约为零。实际上，可以表明，当
Figure BDA0001078613420000174
时，最大功率(对于给定电源电压而言)传送至负载。
图7为示出可传送至负载的功率轮廓对驱动频率和负载电阻(R负载)的关系曲线的轮廓曲线图。如图7所示，可传送的功率随负载电阻和驱动频率而变化。图7还示出可随着负载电阻和驱动频率变化而实现的最大功率传送的线92。因此，功率控制器85可使用R负载的测定值连同定义图7所示线92的存储数据(其可为查找表)来确定待使用的对应驱动频率。以这种方式，微处理器23将在负载电阻在切割/烧灼过程期间变化时沿着图7所示线92跟踪。
此方法的优点之一在于它在低R负载值下，特别是在小于临界值的R负载值情况下(即，当R负载_ref＜2πfLF M时)实现其中即使此值低于期望的功率水平也将传送最大功率的可用的操作条件。然而，沿着最大功率传送的线92操作可导致上述系统极限值中的一些被突破，除非采取进一步行动。在优选实施方案中，此进一步控制行动是使用脉冲跳跃技术，直至平均功率、电流和/或电压低于相关极限值。例如，如由上述测量可见，测定电压和电流处理模块83可确定传送功率、RMS电压和RMS电流。功率控制器85因此可使用这些值来跳过CTRL控制信号的一个或多个脉冲，直至测定电压和电流值低于相关系统极限值，且传送功率等于或低于由医疗装置控制模块89限定的功率设定点。
可例如通过下述方式跳过脉冲：通过逻辑门(未示出)传递由控制信号发生器87产生的脉冲，并且通过控制至逻辑门的另一输入的逻辑电平选择性地抑制由控制信号发生器87产生的脉冲。例如，可通过AND门传递由控制信号发生器87产生的每个控制信号的脉冲，其中AND门的另一输入由功率控制器85产生且当与平常一样待将所述脉冲输出到FET栅极驱动器37时为逻辑“1”，而当待跳过或抑制所述脉冲时为逻辑“0”。当然也可使用其它脉冲跳跃技术。
医疗装置控制模块
如上所述，医疗装置控制模块89控制烧灼/切割装置1的大体操作。它通过用户输入模块91接收用户输入。这些输入可指定夹钳9的钳口现在夹持血管或组织且用户希望开始切割/烧灼并且指定是否待向所述血管/组织施加超声能量或电能。作为回应，在本实施方案中，医疗装置控制模块89启动切割/烧灼控制程序。首先，医疗装置控制模块89向功率控制器85发送启动信号并且获得由测定电压和电流处理模块83确定的负载阻抗量度。医疗装置控制模块89随后检查所获得的负载阻抗以确保所述负载不是开路或短路。如果它不是，则医疗装置控制模块89开始改变功率设定点以进行所期望的切割/烧灼并且设定待产生驱动信号的初始周期/频率。如上所述，对于超声操作而言，驱动信号的初始频率将被设计为大约50kHz且对于射频电操作而言，初始频率将被设定为大约500kHz。
电压/电流感测电路
如图2所示，提供电压感测电路31以感测施加到负载上的负载电压，并且提供电流感测电路33以感测施加到负载上的电流。感测信号供应至微处理器23以用于控制医疗装置的操作。存在感测负载电压和负载电流的各种方式且现在将描述一些这样的方式。
图8a示出第一变压器电路42-1的初级侧和电流感测电路33获得负载电流的量度的一种方式。如图所示，电流感测电路33包括另外的电感器线匝67，另外的电感器线匝67连接存在于电感器47(或电感器49)中且因而输出随负载电流的变化率而变化的电感器67两端的电压的通量。电感器67两端的电压为其振幅与负载电流的变化率和67中的线匝数成正比的双极性电压。此双极性电压通过输出测定电压(Vmeas)的运算放大器电路69-1而被缩放和转换成适于输入到微处理器23的单极性电压。此测定电压也会依从于在电感器47中流动的电流且因此也会依从于在变压器电路42-1的次级侧上流动的电流且因此流动穿过负载的电流。当已知电感器47与电感器67的线匝数的比率时，测定电压和电流处理模块83可使用Vmeas来确定电感器47两端的电压。电感器47两端的电压与流动穿过电感器47的电流相关成V＝Ldi/dt。当已知电感器47的电感时，测定电压和电流处理模块83可通过下述方式来确定在变压器电路42-1的初级侧中流动的电流：对电感器47两端的电压进行积分，并且对结果进行缩放以虑及电感器47的电感(和运算放大器电路69-1的缩放)。此电流量度随后可通过另一缩放以虑及电感器49与电感器53之间的线匝数而被转换成负载电流(iL)的合适量度。当然，测定电压和电流处理模块83不需要对电感器47两端的电压进行积分－因为测定信号为正弦的且因此积分可通过应用合适的缩放因子和90度相移来实现。因此，测定电压和电流处理模块83可通过下述方式来确定负载电流：对测定电压(Vmeas)应用合适的(预先存储的)缩放因子并且应用合适的90度相移(其可仅通过如上所述交换I样品和Q样品的次序来实现)。
图8b示出第一变压器电路41-1的初级侧和电流感测电路33可获得负载电流的量度的另一种方式。如图所示，在这种情况下，电流感测电路33测量电容器45两端的电压。电容器45两端的电压为双极性电压。此双极性电压通过输出测定电压(Vmeas)的运算放大器电路69-2而被缩放和转换成适于输入到微处理器23的单极性电压。通过I＝CdVmeas/dt且因此流动穿过负载的电流使此电压与在变压器电路42的初级侧中流动的电流相关。当已知电容器45的电容时，测定电压和电流处理模块83可通过下述方式来确定在变压器电路42-1的初级侧中流动的电流：对电容器45两端的电压进行微分并对结果进行缩放以虑及电容器45的电容(和运算放大器电路69-2的缩放)。此电流量度随后可通过另一缩放以虑及电感器49与电感器53之间的线匝数而被转换成负载电流(iL)的合适量度。当然，测定电压和电流处理模块83不需要对电容器45两端的电压进行微分－因为测定信号为正弦的且因此微分可通过应用合适的缩放因子和90度相移来实现。因此，测定电压和电流处理模块83可通过下述方式来确定负载电流：对测定电压(Vmeas)应用合适的(预先存储的)缩放因子并且应用合适的90度相移(其可仅通过如上所述交换I样品和Q样品的次序来实现)。
图8c示意性地示出如何可确定负载电压的量度。图8c示出第一变压器电路42的次级侧并且示出对分配器电路(在这种情况下由电阻器R1和R2形成)的使用，其中电阻器R2两端的电压输入到运算放大器电路69-3。因此，通过对来自运算放大器69-3的测定电压应用适当的缩放，测定电压和电流处理模块83可确定负载电压。
上述感测电路使用运算放大器电路69来将双极性驱动信号转换成适于输入到微处理器23的单极性电压。对此种运算放大器电路的使用具有多个缺点，包括它们是昂贵的，它们消耗功率而且它们需要电子器件内的空间。当所述装置被设计成电池供电且所述电子器件容纳在所述装置的柄部5内时，这些都是重要的因素。图9示出可在没有运算放大器的情况下使用的各种感测电路。当交流驱动信号为单极性的时，图9a的电路是合适的。这可通过用半桥信号发生器置换全桥信号发生器27来实现。这将意味着移除例如将节点B连接至接地的FET 41-3和41-4。在这种情况下，微处理器23只需要产生一个控制信号(CTRL1)来控制FET 41-1和41-2。图9b的电路适于单极性信号和双极性驱动信号两者。
在图9a中，电容器45已被移动成位于形成变压器电路42-1的初级的电感器49与接地(GND)之间。电流感测电路33被布置成通过由电阻器R1//R2和R3形成的分配器来测量电容器45两端的电压。电阻器R1通过开关121将直流阻塞电容器CB的输出连接至微处理器23的电源电压轨(在这种情况下处于3.3V下)；且电阻器R2将直流阻塞电容器CB的输出连接至参考电位(在这种情况下为接地)。电阻器R1和R2因此提供向测定交流信号施加直流偏压的分配器电路。直流阻塞电容器防止此直流偏压联接至驱动电路。通常，电阻器R1和R2相等，使得直流偏压将处于1.65V下。因此，从感测电路33输出的电压将为具有约1.65V的中间轨值且其峰值电压将为电容器45两端的电压的一部分的交流电压。由电阻器R1//R2和R3形成的分配器是如此以致于传递至微处理器23的交流信号的峰到峰振幅小于微处理器23的3.3V输入范围。如果微处理器23在不同的电路轨(例如5V)下操作，则可相应地调节电阻器R1、R2和R3的值。为使从3.3V轨或从变压器电路42-1消耗的电流最小化，电阻器R1、R2和R3可具有相对大的值且这些电阻器的典型值为：R1＝R2＝200Ω且R3＝1000Ω。R1和R2的值应被选择成满足用于对所述信号进行采样的模/数转换器的输入阻抗要求。开关121允许微处理器23使感测电路33与3.3V轨断开连接－以使得当不需要感测时，电路33不消耗任何功率。
图9b示出可在变压器电路42-1的次级侧上提供类似电路的方式。具体地讲，图9b示出用于通过由电容器C1和C2形成的分配器获得负载电压VL的量度的电压感测电路31。如果用电阻器置换电容器C1和C2，则应在以图9a所示方式由电阻器R1和R2形成的分配器电路之前提供阻塞电容器CB。图9b还示出通过下述方式来感测负载电流的电流感测电路33：通过由电阻器R4//R5和R6形成的分配器来感测电容器C3两端的电压。如图所示，提供直流阻塞电容器CB以使得能够通过由电阻器R4和R5形成的分配器电路向微处理器的输出添加直流偏压信号。如前所述，开关121-1和121-2允许微处理器在不需要传感器信号时关断感测电路31和33。如本领域的技术人员将了解，图9所示的“无运算放大器”感测电路31和33制造成本更低，可被制造成比图8所示的运算放大器电路消耗更少的功率，且占据电路板上的更少的空间。
图8和图9所示的电路用于从驱动电路29的第一变压器电路42-1获得测量。如本领域的技术人员将了解，相同或相似的感测电路将被提供用于感测第二变压器电路42-2中的信号。此外，尽管图9所示的感测电路感测电容器两端的电压，但所述电路也可感测另一阻抗元件上的电压，例如变压器电路42的电阻器上的电压。
主动电池保护
通常，对于电池驱动装置，例如上文所述的医疗装置1，在电池与电路之间提供熔丝，以保护电池免受由短路等造成的损坏。然而，标准熔丝具有约10毫欧的电阻。对于这种标准熔丝，当从电池消耗10A时，通过熔丝耗散大约1W。现在参照减少与此类标准熔丝相关的功率耗散的图10来描述本实施方案中使用的主动熔丝电路130。
图10示出向图3所示电路供应14V轨和GNG轨的电池15。主动熔丝电路130包括差分放大器131，差分放大器131测量连接在14V轨与电池(Vbat+)的正极端子之间的PCB导体迹线133的一部分两端的电压降。导体迹线133具有大约1-2毫欧的电阻且因此电压降与从电池15消耗的电流成比例。测定电压降由低通滤波器135低通滤波以避免触发熔丝电路的瞬态尖峰－以使其仅为对应将穿过滤波器135的从电池15消耗的直流电流的电压。在本实施方案中，低通滤波器135具有约10Hz的截止频率。然后使用锁存比较器137来比较来自低通滤波器135的输出与基准电压(Vref)。预先将基准电压设定成对应从电池消耗的电流的期望极限值。在本实施方案中，将Vref设定成对应15A的电流极限值。当迹线133两端的电压降小于基准电压时，比较器137的输出保持处于高值下－所述高值使FET开关139保持接通且因此桥信号发生器27可从电池15消耗电流。然而，当迹线133两端的电压降大于基准电压时，则比较器137的输出变低且其保持低，即使从电池消耗的电流降至低于限定极限值。当比较器输出为低时，关断FET 139，从而使电池15与至少桥信号发生器27断开连接。
在本实施方案中，FET 139为具有仅2毫欧的接通电阻的N沟道增强模式开关。这意味着当开关139接通且从电池消耗10A时，通过开关139耗散仅0.2W。
在本实施方案中，当比较器137被触发且开关139断开(开路)时，必须移除电池15以重设主动熔丝电路130－因为开关139的断开使除主动熔丝130的电路部件以外的所有电子器件与电池断开连接。作为另外一种选择，如果直接从电池对微处理器23(或一些其它控制电路)提供功率，则可响应于用户输入(例如响应于用户按下重设按钮或诸如此类)或响应于某一其它触发事件(例如在预定逾时周期之后)重设比较器137。
修改和替代
上文已描述了一种医疗烧灼/切割装置。本领域的技术人员将会知道，可进行多种修改，现在对这些修改中的一些进行描述。其它修改对于本领域的技术人员将显而易见。
在上述实施方案中，描述了各种操作频率、电流、电压等。如本领域的技术人员将了解，确切电流、电压、频率、电容器值、电感器值等均可根据应用来加以改变且上文所述的任何值不应被视为以任何方式限制。然而，概括来讲，上述电路已被设计成向医疗装置提供驱动信号，其中传送功率期望为至少10W且优选地在10W与200W之间；传送电压期望为至少20VRMS且优选地在30VRMS与120VRMS之间；传送电流被设计为至少0.5ARMS且优选地在1ARMS与2ARMS之间；且用于超声操作的驱动频率期望为至少20kHz且优选地在30kHz与80kHz之间；且用于射频操作的驱动频率期望为至少100kHz且优选地在250kHz与1MHz之间。
在上述实施方案中，谐振电路43-1和43-2是由电容器-电感器-电感器元件形成。如本领域的技术人员将了解，也可使用具有呈各种串联和并联构型的多个电容器和电感器的其它谐振电路设计或更简单的LC谐振电路。此外，在一些应用中，不需要变压器来递升驱动电压，因为FET可传送所需的驱动电压。
图1示出了一种方式，其中电池和控制电子器件可安装到医疗装置的手柄中。本领域的技术人员将会知道，手柄的形状因子可采取多种不同的设计。实际上，所述装置为电池供电的并不重要，但这对于一些应用无需使用电源线等是优选的。
上述实施方案包括对各种新颖特征结构的描述，包括选择性地向被夹钳夹持的组织施加超声能量或射频能量的新颖能力、在电操作模式下微处理器控制所述装置的操作的新颖方式、测量负载电流/电压的方式以及使用主动熔丝电路来保护电池的方式。如本领域的技术人员将了解，不需要同时采用这些新颖特征结构。例如，上述电流/电压感测技术可如主动熔丝电路一样与其它装置一起使用。相似地，通过跟踪最大功率传送条件和通过使用脉冲跳跃技术来控制电操作模式的方式可用于没有超声换能器的装置。
在上述实施方案中，描述了用于对被夹钳夹持的血管或组织进行切割/烧灼的示例性控制算法。如本领域的技术人员将了解，可使用各种不同的程序且读者参考描述此种切割/烧灼装置的操作的文献以获取更多细节。
在上述实施方案中，使用了四个FET开关来将由电池提供的直流电压转换成处于期望频率下的交变信号。如本领域的技术人员将了解，没有必要使用四个开关－也可以使用两个开关(使用半桥电路)。另外，尽管使用了FET开关，但也可以使用其它切换装置，例如双极性晶体管开关。然而，MOSFET是优选的，因为其在上述频率和电流水平下操作时低损耗的优越性能。
在上述实施方案中，在超声操作模式下，I和Q采样电路81对感测电压/电流信号进行过采样且在电操作模式下，对感测电压/电流信号进行欠采样。本领域的技术人员将会知道，这并不重要。由于采样的同步性质，如果需要可每周期不止一次或每n个周期一次获取样品。上述实施方案中使用的采样速率被选择成使测量提供给功率控制器85和医疗装置控制模块89的速率最大化，因为这允许在烧灼过程期间更好地控制所施加的功率。
在上述实施方案中，提供了14V直流电源。在其它实施方案中，可提供更低(或更高)的直流电压源。在这种情况下，可提供更大(或更小)的变压器线匝比以使负载电压升高至期望的电平或者可使用更低的操作电压。
在上述实施方案中，医疗装置被布置成向被夹钳夹持的组织/血管传送期望的功率(呈超声能量或电能的形式)。在另选的实施方案中，装置可被布置成向超声换能器或夹钳传送期望的电流或期望的电压电平。
在上述实施方案中，电池示出为整合到医疗装置。在另选的实施方案中，可将电池包装以夹在外科医生的束带上，或只是放置在Mayo架上。在本实施方案中，相对较小的两个导体电缆可将电池组连接至医疗装置。
在上述实施方案中，提供了基于微处理器的控制电路。这因可使用适当的计算机软件来将微处理器编程为进行上述控制动作的简易性而为优选的。此类软件可提供在例如CD-ROM等有形载体上。作为另外一种选择，代替上述基于微处理器的电路，可使用硬件控制电路。
在上述实施方案中，用户控制传送至血管/组织的能量是超声能量还是射频电能。在另选的实施方案中，微处理器可基于内部产生的控制信号或响应于从另一装置接收到的控制信号而控制选择。
在上述实施方案中，主动熔丝电路断开开关以使桥信号发生器与电池断开连接。在另选的实施方案中，主动熔丝电路也可接入电池与桥信号发生器之间的大阻抗以限制从电池消耗的电流。此外，开关可用于使正电压电源与信号发生器断开连接，而不是断开电池的负极端子。

Claims (17)

1.一种用于具有超声换能器和端部执行器的医疗装置的电子设备，所述电子设备包括：
驱动电路，所述驱动电路用于产生具有驱动频率的周期性驱动信号；和
控制器，所述控制器能够操作以控制所述驱动电路；
所述驱动电路包括具有第一谐振频率的第一谐振电路和具有不同于所述第一谐振频率的第二谐振频率的第二谐振电路，并且其中所述控制器能够操作以控制所述驱动电路，使得当驱动信号待施加到所述超声换能器时，所述驱动电路产生具有对应于所述第一谐振频率的频率的驱动信号，并且使得当周期性驱动信号待施加到所述端部执行器时，所述驱动电路产生具有对应于所述第二谐振频率的频率的驱动信号，
其中，所述控制器被布置成围绕所述第一谐振频率或第二谐振频率改变所述驱动信号的周期，以改变供应至所述端部执行器夹持的组织的能量；以及
其中所述控制器被布置成改变所述驱动信号的周期以使所述驱动频率移动远离所述第一谐振频率或第二谐振频率，从而降低供应至所述端部执行器夹持的血管或组织的能量。
2.一种医疗装置，包括：
端部执行器，所述端部执行器用于夹持组织；
超声换能器，所述超声换能器联接至所述端部执行器；和
根据权利要求1所述的电子设备。
3.根据权利要求2所述的医疗装置，其中所述第一谐振频率对应于所述超声换能器的谐振特性。
4.根据权利要求2所述的医疗装置，包括联接在所述控制器与所述驱动电路之间的信号发生器，所述信号发生器用于依据来自所述控制器的控制信号从直流电压电源产生周期性变化的电压并且用于将所述周期性变化的电压供应至所述驱动电路的所述第一谐振电路和所述第二谐振电路。
5.根据权利要求2所述的医疗装置，其中所述控制器被构造成能够改变所述驱动信号的所述周期，使得所述驱动信号的频率围绕所述第一谐振频率在所述第一谐振频率的0.1％至1％的范围内变化，或者使得所述驱动信号的频率围绕所述第二谐振频率在所述第二谐振频率的40％至60％的范围内变化。
6.根据权利要求2所述的医疗装置，其中所述第一谐振电路和所述第二谐振电路的谐振特性随被夹钳夹持的所述组织而变化，并且其中所述控制器被构造成能够改变所述驱动信号的所述周期以跟踪相应谐振特性的变化。
7.根据权利要求2所述的医疗装置，还包括超声波导，所述超声波导联接至所述超声换能器，用于将由所述超声换能器产生的超声能量朝向所述端部执行器引导；其中所述端部执行器包括第一钳口和第二钳口，并且其中所述第二谐振电路电联接至所述端部执行器的所述第一钳口和所述第二钳口。
8.根据权利要求7所述的医疗装置，其中所述端部执行器的所述第一钳口电联接至所述波导，并且其中所述第二谐振电路通过所述超声波导电联接至所述端部执行器的所述第一钳口。
9.根据权利要求7所述的医疗装置，其中所述第一谐振电路电联接至所述超声换能器并且电联接至所述波导。
10.根据权利要求2所述的医疗装置，包括感测电路，所述感测电路用于感测施加到所述超声换能器或施加到所述端部执行器上的周期性驱动信号。
11.根据权利要求10所述的医疗装置，其中所述第一谐振电路和所述第二谐振电路中的一者或两者包括电感器线圈、电容器和电阻器中的至少一者，并且其中所述感测电路包括运算放大器电路，所述运算放大器电路用于感测所述电感器线圈或所述电容器或所述电阻器上的电压并且用于将感测到的电压转换为适于输入到所述控制器的传感器信号。
12.根据权利要求10所述的医疗装置，其中所述第一谐振电路和所述第二谐振电路中的一者或两者包括连接在所述谐振电路与参考电位之间的阻抗元件，并且其中所述感测电路包括分配器电路和偏压信号发生器，所述分配器电路用于获得所述阻抗元件上的电压的量度，所述偏压信号发生器用于向所述电压量度施加直流偏压信号。
13.根据权利要求12所述的医疗装置，其中所述阻抗元件包括电容器或电阻器。
14.根据权利要求12或13所述的医疗装置，其中所述感测电路包括直流阻塞电路，所述直流阻塞电路用于防止来自所述偏压信号发生器的所述直流偏压信号与所述驱动电路联接。
15.根据权利要求12或13所述的医疗装置，其中所述分配器电路连接在基准电压与所述控制器的电源电压之间。
16.根据权利要求2所述的医疗装置，包括对所述装置提供功率的一个或多个电池，并且还包括用于保护所述一个或多个电池的主动熔丝电路。
17.根据权利要求16所述的医疗装置，其中所述主动熔丝电路包括开关和控制电路，所述开关电联接在所述一个或多个电池的端子与所述驱动电路之间，所述控制电路被构造成能够断开所述开关以使所述一个或多个电池的端子与所述驱动电路隔离。
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