CN102481167B - 高频手术刀生成器以及用于运行高频手术刀生成器的方法 - Google Patents
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Abstract
为了在高频手术刀生成器中能够突然结束输出信号，迄今为止使用欧姆负载。现在推荐一种高频手术刀生成器，该高频手术刀生成器包括具有至少一个储能电容器的电源设备，具有至少一个储能器的可控开关装置，该储能器例如是变压器，通过该可控开关装置产生能输送给高频手术器械的高频输出信号，其中在储能器和储能电容器之间接入反馈装置，此外使用控制器，该控制器控制开关装置和反馈装置，使得在应当结束高频输出信号时将反馈装置至少暂时导通并且将储能器至少部分放电到储能电容器之中。
Description
技术领域
本发明涉及一种根据权利要求1的前序部分的高频手术刀生成器以及一种用于运行所述高频手术刀生成器的方法。
背景技术
高频手术刀生成器越来越多地用于切割和凝结组织。与机械切割相比，高频手术切割的优点之一可在切口边缘的止血中看到，该止血尤其是通过热凝结实现。凝结区的深度在此主要取决于所治疗的组织的出血情况，因此对高频手术刀生成器的要求就是能够以尽量可重现的方式调整凝结区的深度。在此重要的尤其是高频手术刀生成器的高频输出信号的波形，而且尤其是峰值与有效值之比。为此选用经过振幅调制的高频电压(电流)，其中调制被进行得使得高频手术刀生成器应当尽可能还仅产生唯一一个振荡周期-随后是较长的间隔时间。
另一个要求就是要保证高频手术刀生成器有尽可能高的效率，因为如果效率较低就必须通过复杂的冷却措施来消除热损耗，这是手术室中不希望出现的情况。
DE10046592A1公开了一种通过以下方式获得较高效率的高频手术刀生成器：可以使得在这类高频手术刀生成器中通常设置的直流电源在两种工作方式下工作，而且是一方面(常规地)用于给功率振荡器供电，另一方面这样运行，即将供应给功率振荡器的能量送回到直流电源的输入端。这里并没有在短脉冲的形成方面实现多大改进。
DE10046592A1公开了一种根据权利要求1前序部分的高频手术刀生成器。在该生成器中，当应当结束高频输出信号时会通过也就是与负载并联的欧姆电阻从输出电路提取能量。该设备的效率很低。
发明内容
本发明的任务在于，展示一种开头所述类型的高频手术刀生成器以及一种用于运行该高频手术刀生成器的方法，能够精确迅速地形成高频输出信号，同时还能实现很高的效率。
采用权利要求1所述的高频手术刀生成器以及权利要求13所述用于运行该高频手术刀生成器的方法来解决这一任务。
尤其采用这样一种高频手术刀生成器解决所述任务，所述高频手术刀生成器包括具有至少一个储能电容器的电源设备、具有至少一个储能器(例如输出变压器)的可控开关装置，通过该可控开关装置产生可输送给高频手术器械的高频输出信号，其中在储能器和储能电容器之间接入反馈装置，并且设置控制器，所述控制器控制开关装置和反馈装置，使得在应当结束高频输出信号时使得反馈装置至少暂时导通，并且使得储能器至少部分地放电到储能电容器之中。
因此本发明的要点在于：从储能器中提取在通常设置的无功元件(例如通常设置的输出变压器)中储存的电能或磁能，由此使得高频输出信号迅速归零。输送给电源设备的储能电容器的该能量之后就可供下一个高频输出信号使用，这提高了装置的效率。
如果设置从储能器中排出剩余能量的放电装置，就能改善信号可控性，同时减小电路复杂性。为此也可以通过欧姆负载转换成热量，从而保证振荡器可靠衰减。但仍然可通过反馈显著提高效率。因此，优选由控制器控制放电装置，使得在储能器部分放电之后排出剩余能量。
在一种优选实施方式中，储能器包括输出变压器，反馈装置包括输出变压器上的独立绕组。以这种方式很容易调整出期望的电压比。
可以通过由控制器控制的电子开关实现反馈。替换的，可以通过二极管线路进行反馈，在高频输出信号结束时通过该二极管线路将储能器放电。
优选这样布置高频手术刀生成器的储能电容器，使其能够在中间接入控制元件的条件下吸收输出变压器的多余能量。
反馈装置包括DC/DC变换器，以便能够进行相应的电压匹配。可以将该变换器构造成升压变换器。
在一种替换实施方式中，反馈装置包括降压变换器，利用电子开关将该降压变换器的输入电压调节到恒定电压。这种电路的构造特别简单。
用于运行高频手术刀生成器的方法，所述高频手术刀生成器包括具有至少一个储能电容器的电源设备、可控开关装置以及用以产生高频输出信号输送给高频手术器械的输出变压器，所述方法的特征在于，为了切断高频输出信号，将储存在输出变压器中的能量输送给储能电容器，并且储存在该储能电容器中。以上已经解释了该方法的优点。凡是能够根据上述电路特征识别出来的该方法的相应改进均具有这些优点。
附图说明
以下将根据附图对本发明的实施例进行详细解释。相关附图如下：
附图1示出本发明第一种实施方式的电路图；
附图2示出本发明第二种实施方式的电路图；
附图3示出本发明第三种实施方式的电路图；
附图4示出本发明第四种实施方式的电路图；
附图5示出信号流的时序图；以及
附图6示出本发明第五种实施方式的电路图。
在以下说明部分中将相同的附图标记用于相同或作用相同的部件。
具体实施方式
在附图1所示的电路中以附图标记10表示电源设备，仅仅绘出了电源设备中的DC/DC变换器和位于输出端的电容器C。当然还设置其它一些用来从交流电网给DC/DC变换器供电的变换器装置。
生成器包括振荡电路CR和输出变压器TR的(初级)绕组W1，并且通过晶体管T2与电容器C相连。晶体管T2的控制输入端b与控制器20相连，因此控制器可以通过相应地控制晶体管T2而在振荡电路CR-W1中产生振荡，通过次级线圈WA和串联振荡电路LA、CA将该振荡作为输出电压Ua转移给(图中没有绘出的)高频手术器械。
变压器TR的另一个绕组W2一端经由二极管D1和晶体管T1与电容器C相连、另一端经由直通导线同样与电容器C相连。晶体管T1的控制输入端a与控制器20相连。电阻R与晶体管T3(其控制输入端c同样与控制器20相连)构成的串联电路与另一个绕组W2并联。
以下将借助附图5解释根据附图1的电路的工作原理。
控制器20产生控制脉冲n和n+1，将这些控制脉冲传输给晶体管T2的控制输入端b。通过控制晶体管T2激励振荡电路CR、W1并且产生输出电压Ua。
控制器20产生使得晶体管T1导通的信号a，用于使振荡电路CR、W1结束振荡。因此通过二极管D1和晶体管T1仅将另一个绕组W2与电容器C相连，从而使得电流I1流过，该电流将储存在变压器TR中的能量转移到电容器C之中。
经过比较短的控制脉冲a之后(参见附图5)，控制器20通过晶体管T3的控制输入端c使得晶体管T3导通，从而电流I2现在流过电阻R，由此将来自变压器TR的能量的剩余放电转变为热量。这样就使得输出电压Ua完全归零，其中储存在输出变压器TR中的大部分能量在电容器C上重新可供使用，以便重新用于下次通过控制脉冲b(脉冲n+1)使得晶体管T2导通。
根据附图2的电路在电源设备10和输出电路方面与根据附图1的电路构造相同。在该电路中，变压器TR的初级绕组W1通过晶体管T21与电容器C的上极相连，并且通过晶体管T22与电容器C的下极相连。两个晶体管T21和T22的集电极-发射极线路通过空转二极管桥接。
下方晶体管T22的集电极通过二极管D3与电容器C的上极相连。晶体管T21的发射极通过二极管D2与电容器C的下极相连，其中通过由电阻R和晶体管T3构成的串联电路桥接二级管D2。
为了解释根据附图2的电路的功能而说明电流路径。
当晶体管T21和晶体管T22导通时，就会形成产生(脉冲波形的)输出电压Ua的电流路径4。为了使该输出脉冲迅速结束，(在晶体管T21、T22接通之后)通过二极管D2和D3将包含在变压器TR中的能量作为电流I1送回到电容器C。为了泄放剩余能量，控制器20控制晶体管T3，使得包含在变压器TR中的剩余能量作为经由电流路径6的电流I2转变成热量。
附图3所示的装置在振荡产生装置和变压器TR方面类似于根据附图1的电路。但是在该装置中附加绕组W2通过包括二极管D1、电容器CH、电感LH和另一个二极管DH的升压变换器与电容器C相连。更为准确地说，由二极管D1和电容器CH构成的串联电路与附加绕组W2并联。线圈LH的一端位于该二极管和该电容器之间的耦合点上，线圈LH的另一端通过二极管DH与电容器C相连。二极管DH和电感LH之间的耦合点通过晶体管T1与电容器C的另一极相连。
此外还将由欧姆电阻R和晶体管T3构成的串联电路与附加绕组W2并联。
按照附图5所示的时序图进行控制，但也可以按照以下所述不同于附图5所示的方式来控制反馈晶体管T1：
这里所示由LH、T1和DH构成的电路是升压变换器。该升压变换器能够将能量从储能电容器CH转移到输入电容器C。可以用脉宽调制(PWM)、电流模式调节或者类似的准连续工作方式来控制晶体管T1。调节升压变换器的宗旨是使得储能电容器CH上的电压保持恒定并且相应地改变经过LH的扼流圈电流。
附图4所示电路与根据附图3的电路的区别在于：并不使用在实际生成器电路中设置的电容器C，而是使用在中间电路中设置的电容器Cz来通过电流I1反馈储存在变压器TR中的能量。从该电路也可看出，在本发明中吸收储存在输出变压器TR中的能量并且将其又用于重新激励和产生输出电压Ua的元件并不重要。
附图6所示的电路中重新设置晶体管T2来激励和产生输出电压Ua，当通过来自控制器20的信号b进行控制时，该晶体管T2就会使得电源设备10的输出电容器C和变压器TR的初级绕组W1之间的电路闭合。
为了将变压器TR中所包含的能量反馈到电容器C，在该装置中将由第一二极管D11、第二二极管D12、晶体管T1和线圈LT构成的串联电路与电容器C相连。晶体管T1和线圈LT之间的连接点通过二极管DT与电容器C的下极相连。二极管D12和晶体管T1之间的耦合点通过电容器CT与电容器C的下极相连。二极管D12和D11之间的连接点通过由电阻R和晶体管T2构成的串联电路与电容器C的上极相连。
在该电路中，用于反馈的晶体管T1通过其控制输入端a由控制器20在PWM模式下(或者在另一种受控模式下，例如电流模式或者两点调节)驱动，而且使得这里构造的降压变换器的输入电压调节为对电容器C进行充电的恒定电压。否则该电路就如同之前所述的电路一样被驱动，其中在该电路(如附图2所示)中生成器也不是正弦振荡的生成器，而是为单脉冲激励设计的。因此这里也省去了与初级绕组W1并联的电容器。所反馈的能量在这里限于储存在变压器中的磁化能。
Claims (17)
1.一种高频手术刀生成器，包括
-具有至少一个储能电容器的电源设备；
-具有至少一个储能器的可控开关装置，通过该可控开关装置产生能输送给高频手术器械的高频输出信号（Ua），
其特征在于，
在储能器（TR）和储能电容器（C）之间接入反馈装置（D1，D2，D3，P1，DH，LH，W2），并且设置控制器（20），该控制器控制开关装置（T2）和反馈装置（D1，D2，D3，P1，DH，LH，W2），使得在应当结束高频输出信号（UH）时将反馈装置（D1，D2，D3，P1，DH，LH，W2）至少暂时导通并且将储能器（TR）至少部分放电到储能电容器（C）之中以便对储能电容器（C）充电。
2.根据权利要求1所述的高频手术刀生成器，其特征在于，该储能器是变压器。
3.根据权利要求1所述的高频手术刀生成器，其特征在于，设置放电装置（R，T3），用于从储能器（TR）中排出剩余能量。
4. 根据权利要求3所述的高频手术刀生成器，其特征在于，所述放电装置包括转换装置，用来将剩余能量转变成热量。
5. 根据权利要求4所述的高频手术刀生成器，其特征在于，所述转换装置为欧姆负载（R）。
6. 根据权利要求3-5之一所述的高频手术刀生成器，其特征在于，控制器（20）控制放电装置，使得在储能器（TR）部分放电之后排出剩余能量。
7. 根据权利要求1-5之一所述的高频手术刀生成器，其特征在于，储能器包括输出变压器（TR），而反馈装置包括输出变压器（TR）上的独立绕组（W1）。
8. 根据权利要求1-5之一所述的高频手术刀生成器，其特征在于，反馈装置包括至少一个由控制器（20）进行控制的电子开关（T1）。
9. 根据权利要求1至5之一所述的高频手术刀生成器，其特征在于，反馈装置包括二极管线路（D2，D3），在高频输出信号（Ua）结束时通过该二极管线路对储能器（TR）放电。
10. 根据权利要求1-5之一所述的高频手术刀生成器，其特征在于，储能电容器（C）与开关装置的输出变压器（TR）串联。
11. 根据权利要求1至5之一所述的高频手术刀生成器，其特征在于，储能电容器（Cz）布置在开关装置的DC/DC变换器之前。
12. 根据权利要求1所述的高频手术刀生成器，其特征在于，反馈装置包括DC/DC变换器。
13. 根据权利要求1所述的高频手术刀生成器，其特征在于，反馈装置包括升压变换器。
14. 根据权利要求1-5之一所述的高频手术刀生成器，其特征在于，反馈装置包括降压变换器，利用电子开关（T1）将该降压变换器的输入电压调节为恒定电压。
15. 根据权利要求12或13所述的高频手术刀生成器，其特征在于，以脉宽调制方式控制反馈装置。
16. 根据权利要求12或13所述的高频手术刀生成器，其特征在于，以电流模式调节方式控制反馈装置。
17. 一种用于运行如权利要求1-16之一所述的高频手术刀生成器的方法，所述高频手术刀生成器包括具有至少一个储能电容器的电源设备和具有输出变压器的可控开关装置，该输出变压器产生能输送给高频手术器械的高频输出信号，其特征在于，为了切断高频输出信号，将储存在输出变压器中的能量输送给储能电容器并且储存在该储能电容器中。
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| DE102009019373.1 | 2009-04-29 | ||
| DE102009019373 | 2009-04-29 | ||
| DE102009037693.3A DE102009037693B4 (de) | 2009-08-17 | 2009-08-17 | HF-Chirurgiegenerator und Verfahren zum Betreiben eines HF-Chirurgiegenerators |
| DE102009037693.3 | 2009-08-17 | ||
| PCT/EP2010/002186 WO2010124785A1 (de) | 2009-04-29 | 2010-04-07 | Hf-chirurgiegenerator und verfahren zum betreiben eines hf-chirurgiegenerators |
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| CN102481167A CN102481167A (zh) | 2012-05-30 |
| CN102481167B true CN102481167B (zh) | 2015-06-17 |
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| EP (1) | EP2424458B1 (zh) |
| JP (2) | JP2012525169A (zh) |
| CN (1) | CN102481167B (zh) |
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- 2010-04-07 WO PCT/EP2010/002186 patent/WO2010124785A1/de active Application Filing
- 2010-04-07 US US13/266,896 patent/US9314291B2/en not_active Expired - Fee Related
- 2010-04-07 JP JP2012507618A patent/JP2012525169A/ja active Pending
- 2010-04-07 CN CN201080019177.6A patent/CN102481167B/zh not_active Expired - Fee Related
- 2010-04-07 PL PL10713140T patent/PL2424458T3/pl unknown
- 2010-04-07 EP EP10713140.1A patent/EP2424458B1/de active Active
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| DE10046592A1 (de) * | 2000-09-20 | 2002-04-04 | Erbe Elektromedizin | Verfahren und Vorrichtung für die Hochfrequenz-Chirurgie |
Also Published As
| Publication number | Publication date |
|---|---|
| WO2010124785A1 (de) | 2010-11-04 |
| JP2015120037A (ja) | 2015-07-02 |
| US9314291B2 (en) | 2016-04-19 |
| JP2012525169A (ja) | 2012-10-22 |
| US20120053578A1 (en) | 2012-03-01 |
| JP6050412B2 (ja) | 2016-12-21 |
| EP2424458B1 (de) | 2019-06-05 |
| EP2424458A1 (de) | 2012-03-07 |
| CN102481167A (zh) | 2012-05-30 |
| PL2424458T3 (pl) | 2019-09-30 |
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