JP2960971B2 - 電気外科用ゼネレータのための射出火花制御 - Google Patents

電気外科用ゼネレータのための射出火花制御

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Publication number
JP2960971B2
JP2960971B2 JP9500259A JP50025997A JP2960971B2 JP 2960971 B2 JP2960971 B2 JP 2960971B2 JP 9500259 A JP9500259 A JP 9500259A JP 50025997 A JP50025997 A JP 50025997A JP 2960971 B2 JP2960971 B2 JP 2960971B2
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output
waveform
generator
signal
voltage
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JPH10507394A (ja
Inventor
ベック，ロビン・ビー
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Valleylab Inc
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Valleylab Inc
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • 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
    • A61B18/12—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body by heating by passing a current through the tissue to be heated, e.g. high-frequency current
    • A61B18/1206—Generators therefor
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B2018/00636—Sensing and controlling the application of energy
    • A61B2018/00696—Controlled or regulated parameters
    • A61B2018/00732—Frequency
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B18/00—Surgical instruments, devices or methods for transferring non-mechanical forms of energy to or from the body
    • A61B2018/00636—Sensing and controlling the application of energy
    • A61B2018/00773—Sensed parameters
    • A61B2018/00875—Resistance or impedance

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  • Health & Medical Sciences (AREA)
  • Surgery (AREA)
  • Engineering & Computer Science (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • Biomedical Technology (AREA)
  • Molecular Biology (AREA)
  • Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
  • Plasma & Fusion (AREA)
  • Physics & Mathematics (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Medical Informatics (AREA)
  • Otolaryngology (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
  • Public Health (AREA)
  • Veterinary Medicine (AREA)
  • Surgical Instruments (AREA)
  • Generation Of Surge Voltage And Current (AREA)

Description

【発明の詳細な説明】 この明細書に組み入れられて参照文献としてそれの一
部分とされる関連出願が次のとおり同日付けで米国特許
商標局に出願された。
「電気外科用ゼネレータのための電力制御（Power Co
ntrol for an Electrosurgical Generator）」,U.S.S.
N.08/471,116;PC8826. 「神経外科術のための制御システム（A Control Syst
em for Neurosurgery）」U.S.S.N.08/470,533;PC9162. 「電気外科用ゼネレータ電力出力のための制御装置
（Control Apparatus for Electrosurgcal Generator P
ower Output）」,U.S.S.N.08/468,950;PC8827. 「電気外科用ゼネレータのためのディジタル波形発生
（Digital Waveform Generation for Electrosurgical
Generators）」,U.S.S.N.08/471,344;PC9210. 1.発明の分野 この発明は、電気外科ゼネレータに、更
に詳細には、電極が組織から取り去られたときの射出火
花発生の厳しさを低減する電気外科用ゼネレータのため
の設計に関する。
2.開示の背景 電気外科用ゼネレータは、患者の組織に
電力を供給するために手術手順において使用される。電
気外科用ゼネレータは無線周波発生器及びその制御器を
含んでいる。ゼネレータに電極が接続されると、電極は
高周波電気エネルギーで患者の組織を切断し又は凝固さ
せるために使用されることができる。手術中、電流は、
ゼネレータから能動電極を通り、患者の組織及び体液を
通り、帰路電極を通って再びゼネレータへと流れる。こ
れらの電極及び患者により形成された電気回路は患者回
路と呼ばれる。
電気エネルギーは、その波形が組織を切断し又は凝固
させる能力を高めるために整形される、異なった波形は
ゼネレータの異なった動作モードに対応しており、各モ
ードは外科医に種々の手術上の利点を与える。これらの
モードは、切断、凝固、これらの混成、乾燥又は噴霧を
含むことができる。
電気外科用器具の使用の際に遭遇することのある一つ
の問題は、電極が組織から引っ込められるときに電極が
患者に対してアークを生じることである。これは、より
高いインピーダンスが組織により呈示されるにつれて出
力電圧を増大するように設計されている、電気外科用ゼ
ネレータにおける電力制御システムに起因している。こ
れは通常出力電力を維持するために行われる。電極を引
っ込める場合には、電気外科用ゼネレータにおける制御
システムは、まるで組織インピーダンスが劇的に増大し
たかのように機能して電力供給を維持しようとすること
がある。制御システムは電圧を急速に増大し、これによ
り、能動電極が引っ込められるときに、この電極により
組織に対してアークを生じさせることがある。この現象
は「射出火花発生」と呼ばれ、望まれない組織の損傷を
引き起こすので望ましくない。電気外科用ゼネレータの
設計者たちはこの結果を最小限にすることを望んでい
る。
射出火花発生はまた、電気エネルギーが電気外科用ゼ
ネレータにおける最終増幅器段の容量性素子及び誘導性
素子に蓄積されているために発生することがある。たと
え電極が組織から取り去られてゼネレータ出力がオフに
され得るとしても、最終増幅器段に蓄積されたエネルギ
ーは散逸させられなければならない。他の散逸路が利用
可能でなければ、蓄積エネルギーは患者に対してアーク
を生じるかもしれない。
電気外科用ゼネレータに関する初期の設計者たちは射
出火花発生の問題を幾つかの方法で回避した。射出火花
発生を避ける一つの方法は高電圧が能動電極で発生する
のを防止することである。高電圧は出力電圧を能動的に
制御することによって、そうでなければ受動的手段によ
って防止されることができる。多くの初期のゼネレータ
においては、ゼネレータの電気的能力は、負荷のインピ
ーダンスが高いときに、能動電極において高電圧を発生
するのに十分ではなく、従って射出火花発生の問題は受
動的に回避された。
最新の電気外科用ゼネレータにおける閉ループ電力制
御システムは射出火花発生の可能性を高めることがあ
る。出力電力の閉ループ制御は、組織のインピーダンス
が増大されるにつれて、ゼネレータの出力電圧を上昇さ
せることができるであろう。能動電極が組織から取り去
られるときに、負荷の測定インピーダンスは鋭く上昇す
ることがある。閉ループ制御システムはインピーダンス
におけるこの知覚された上昇に応答して電圧を増大す
る。結果として生じる高い出力電圧は射出火花を生じさ
せることができるであろう。
米国特許第4969885号は電気外科用ゼネレータの出力
電圧を制御するための能動的制御装置を開示している。
射出火花発生は、多分（出力電圧ではなく）出力電力を
制御するゼネレータにおける問題であるので、この特許
は射出火花発生の問題を考慮していない。
米国特許第5099840号は負荷のインピーダンスに従っ
てその出力段の共振周波数を調整する電気外科用ゼネレ
ータを開示している。これは出力段の効率を増大するた
めに行われる。射出火花発生の問題はこの特許において
は考慮されていない。この特許とは対照的に、この発明
は、射出火花発生を避けるために利得を減小し、従って
出力段の効率を減小しようと企図されている。これは米
国特許第5099840号とは反対の結果である。
他の米国特許は関連技術を有しているが、いずれも射
出火花制御の問題に向けられていない。米国特許第4658
819号は、電極に供給される電力が直流電源からの電圧
並びに負荷電圧及び電流のセンサにより測定されたよう
な負荷の関数である回路を有している。マイクロプロセ
ッサ制御器が検出信号をディジタル化して負荷インピー
ダンス及び供給されている実際電力を計算する。従っ
て、マイクロプロセッサ制御器は、およそゼネレータが
動作しているかぎり測定、計算及び補正過程を繰り返
す。米国特許第4372315号は。パルスバーストごとの方
式で指定数の無線周波パルスを供給した後に、インピー
ダンスを測定する回路を開示している。米国特許第4321
926号は、電気外科的効果の供給を制御するためのフィ
ードバックシステムを有しているが、インピーダンス検
知は実時間方式ではない。米国特許第3964487号、第398
0085号、第4188927号、及び第4092986号は、負荷インピ
ーダンスの増大に従って出力電流を減小するための回路
部を有している。これらの特許においては、電圧出力が
一定に維持され且つ電流が負荷インピーダンスの増大と
共に減小される。米国特許4094320号は、能動及び帰路
リードにおける電流を検知することにより測定されるよ
うなインピーダンス変化に応答する回路を備えている。
検出電流は互いに減算されて、それが可変の閾値を越え
たならば、ゼネレータはオフにされる。可変の閾値は電
力レベル及び漂遊キャパシタンスによる漏れ電流の関数
である。
この発明の目的の一つは、射出火花発生の問題を克服
すると同時に、なお能動電極における高電力を可能にす
ることである。
発明の要約 射出火花制御システムを含んでいる電気外科用ゼネレ
ータが開示されている。射出火花を制御するための基本
は、諸条件により射出火花が発生しそうなときには、常
に電気外科用ゼネレータの動作に合わせて一時的な調整
を行うことである。これらの調整は、電気外科用ゼネレ
ータの出力を瞬間的に停止して、次に出力段の利得を低
減するために電気外科用ゼネレータの出力段の駆動周波
数を一時的に変えることを含んでいる。
増幅器回路は特定の周波数で効率よく動作するように
同調させられる。異なった周波数で増幅器回路を駆動す
ることは、より低い利得及び効率を呈する「離調」状態
を生じる結果になる。しかしながら、離調状態は電気的
構成部分を緊張させ、従って短い時間の間だけ行われる
べきである。
マイクロコントローラにおけるセンサ及びアルゴリズ
ムは、望ましくは射出火花の発生前の諸条件を検出する
ように要求される。アルゴリズムはまた、事象の順序付
けを制御する、すなわち、まず電気外科用出力を停止し
てアークが始まるのを防止し、次に駆動周波数を適当に
変化させて余剰の蓄積エネルギーを散逸させることが更
に望まれる。出力波形は短時間の間だけ停止されればよ
く、すなわち外科医は組織を切断しながらドラグ（dra
g）を検出することになる。望ましくは、この時間は５
ないし200ミリ秒である。
射出火花が発生する条件を知らせる二つの事象が認め
られている。第１の事象は、電気外科用ゼネレータが患
者の組織を治療するために活動化されていて実際に組織
を治療していることである。これは、電気外科術の開始
のための火花が射出火花制御によって影響されてはいけ
ないので、必要とされる。この第１の事象は、電気外科
用ゼネレータのインピーダンス監視機能によって検知さ
れることができる。望ましくは、インピーダンスが一般
的な動作範囲、例えば4096オームより下、にあるときに
は常に、能動電極は患者の組織にあると考えられる。
第２の事象は、出力電圧が電圧閾値を越えたことを示
す高信号を比較器に出す場合である。射出火花制御に関
する諸条件を検知する別の方法は負荷のインピーダンス
を監視することであろう。閉ループ電力制御システムに
おいて、出力電圧はインピーダンスの増大と共に増大す
るであろう。
典型的には、電圧閾値は通常の動作条件に対して予想
されるピーク電圧の80％に設定されるであろう。電気外
科用ゼネレータは種々のピーク電圧を伴った多くの動作
条件を有しているので、マイクロプロセッサはそのよう
な動作条件をそれぞれに対して適当な電圧閾値を記憶
し、維持し、そして設定する。典型的には、これらの閾
値は主として、外科医が選択した電力設定値、及び動作
のモード、すなわち切断、混成又は乾燥、に依存する。
例えば、切断モードにおける低い電力設定値は低い電圧
閾値を生じる結果になる。しかしながら、電圧閾値はま
た、射出火花を誘発するのに十分に高い一定値であるこ
ともあるであろう。
ある動作モードにおいて、射出火花は外科医に対して
問題を提示しないかもしれない。典型的には、これらの
モードが凝固モード、例えば電気破壊又は噴霧であろ
う。これらのモードのそれぞれにおいて、火花は能動電
極から発生すると予想され、従って、射出火花制御は火
花が供給されるピーク電圧を制御するためにだけ使用さ
れるであろう。
射出火花制御システムは、通常電気外科用ゼネレータ
におけるハードウェア及びソフトウェアの組合せを含ん
でいる。ソフトウェアは射出火花発生に対する諸条件を
決定するための論理的諸段階を実行するように構成され
ることができる。ある電気外科用ゼネレータにおいて、
波形は望ましくはマイクロプロセッサにおいて発生さ
れ、従って、それらにおいて、ある付加的なソフトウェ
アは、射出火花が発生するかもしれないような信号を応
答して、波形の周波数を変更するように要求されるかも
しれない。ハードウェア回路は電圧センサの出力の性質
を検査するために使用されることができる。
図面の簡単な説明 図１は火花制御回路の概略的回路図である。
図２は火花制御システムを備えて電気外科用ゼネレー
タの機能的ブロック図である。
発明の詳細な説明 電気外科用ゼネレータ10は、能動電極12から患者13へ
の患者回路11における火花発生を抑制する射出火花制御
システムを備えている。この射出火花制御システムは、
射出火花発生が起こりそうなときの条件を検出するため
の検出及び論理能力、並びにこれらの条件が検出された
ときに周波数を変更することのできる波形発生器14を備
えている。
電気外科用ゼネレータ10には所望レベルの出力電力を
設定するために外科医に操作される外科医パネル15があ
る。電気外科用ゼネレータ10には、また、外科医パネル
15から所望レベルの出力電力を受けるように電気的に接
続されたマイクロコントローラ16がある。マイクロコン
トローラ16はまた、所望レベルの出力電力に基づいて電
圧閾値を設定することができる。
電気外科用ゼネレータ10における可調整の波形発生器
14は、無線周波波形を発生するために、及びこの波形の
周波数を調整するために使用される。可調整の波形発生
器14は、ディジタル又はアナログ出力を発生するように
設計されることができる。無線周波波形を受けるために
可調整の波形発生器14に無線周波（RF）出力段17が電気
的に接続されている。出力段17は、患者回路11に伝達さ
れる出力電圧及び出力電流を発生するように設計されて
いる。電圧センサ18は、出力電圧を受けるように無線周
波出力段17に接続されていて、出力電圧に比例した第１
信号を発生することができる。
火花制御回路19は、マイクロコントローラ16に電気的
に接続されていて、そこから電圧閾値を受けることがで
きる。火花制御回路19または電圧センサ18に電気的に接
続されていて第１信号を受けることができ、また火花制
御回路19は可調整の波形発生器14に電気的に接続されて
いて、波形の周波数を一時的に停止し次にこれを調整す
ることができる。火花制御回路19は、第１信号が電圧閾
値よりも大きいときに応答して部分的に、一時的停止及
び調整を行う。調整された周波数は無線周波出力段17に
おける利得及び効率の低下を生じさせ、これによって高
電圧が発生するのを防止し且つエネルギーを熱として散
逸させる。
火花制御システムの好適な実施例は、火花制御回路19
及びマイクロコントローラ16を含んでいる。図１に言及
すると、火花制御回路19は、ピーク検出器、比較器、及
びワンショットを有している。ピーク検出器は電圧セン
サ18の出力に接続されている。ピーク検出器は出力電圧
センサ18からの各極大値を記憶するように設計されてい
る。出力電圧センサ18からの信号はピーク検出器に達し
たときには整流されているがフィルタされてはいない。
比較器は、ピーク検出器からのピーク値を受けるよう
に接続され、且つ、図１においてVMAX_CLPと標識付けさ
れた電圧閾値を受けるように接続されている。比較器
は、ピーク値が電圧閾値を越えたときには常に、高信号
を発生するように設計されている。
ワンショットは比較器からの高信号を受けるように接
続されている。ワンショットの目的は、比較器が高信号
を発生するときには常に、マイクロコントローラ16のた
めのパルスを発生することである。このパルスは図１に
おいてSPARK_CONと標識付けされている。マイクロコン
トローラ16はワンショットからのパルスのための入力を
備えている。
好適な実施例において、火花制御回路19は電圧センサ
18の出力を試験するために使用される。出力電圧センサ
18からの整流されているがフィルタされていない波形
は、U17A及びCR11を有するピーク検出器に供給される。
この入力信号は、図１において、VSEN_SCCと標識付けさ
れている。U17Bは、ピーク検出信号の完全性を維持する
ための高インピーダンスバッファである。このバッファ
の出力は除算されて、U16Aを有する比較器に供給され
る。この比較器への他方の入力は、モード及び電力設定
値に依存しているマイクロプロセッサ16において設定さ
れた閾値レベルである。出力電圧のピーク検出標本（サ
ンプル）が閾値を越えると、ワンショットU15Aは点弧さ
れて、マイクロコントローラ16のボードに送られる３ミ
リ秒のパルスを発生する。このパルスは、活動化の最初
の数0.2秒間に発生したならば無視される。そうでなけ
れば、このパルスは、好適な実施例では、５ミリ秒と20
0ミリ秒との間にある期間の間、波形発生器14からの出
力をマイクロコントローラ16により遮断される。
マイクロコントローラ16は火花が制御されたことを検
知する。一実施例においては、マイクロコントローラ16
はモードに依存して遮断時間を調整した。例えば、乾燥
モードにおいては遮断時間は10ミリ秒、又は純粋な切断
モードにおいては100ミリ秒でよいであろう。次にマイ
クロコントローラ16は470KHzの周波数で波形発生器14を
再始動させる。波形発生器14の周波数は、１秒の連続し
た活動化の後、又はゼネレータ10が再び活動化されたと
きには、394KHzに復帰する。
好適な実施例において、マイクロコントローラ16はま
た射出火花発生に先行する諸条件の一つを決定するため
に患者11における負荷のインピーダンスを監視する。そ
れゆえ、好適な実施例において、火花制御回路19は更に
電流センサ20及びインピーダンス測定装置21を含んでい
る。電流センサ20は、出力電流を受けるために無線周波
出力段17に接続されていて、出力電流に比例した第２信
号を発生することができる。インピーダンス測定装置21
は、アナログ回路、又は論理装置、そうでなければマイ
クロプロセッサ準拠式装置であればよい。インピーダン
ス測定装置21は、第１信号及び第２信号を受けるために
並びに患者回路11における負荷のインピーダンスを計算
するために電気的に接続されている。
好適な実施例において、インピーダンスは、射出火花
制御を可能化する事象の発生を決定するためにマイクロ
コントローラ16においてその後使用される。火花制御が
可能化されたならば、マイクロコントローラ16は、出力
段17を約５ミリ秒ないし200ミリ秒の間遮断し、その後
可調整の波形発生器14に波形の周波数を調整するように
信号を送るためのアルゴリズムを有する。
電気外科用ゼネレータ10における射出火花を制御する
方法は、射出火花発生のための条件が存在しているとき
には常に可調整の波形発生器14の周波数を変更して、出
力段17の利得が低下させられるようにする段階を含んで
いる。好適な実施例において、この方法は更に、出力負
荷のインピーダンスを監視すること、出力電圧を監視す
ること、電圧閾値を設定すること、及びインピーダンス
が約4096オームより小さく且つ電圧が電圧閾値より高い
ときには常に火花制御システムをトリガすることの諸段
階を含んでいる。
射出火花発生を制御するための方法におけるその他の
段階には、外科医パネル15上で所望レベルの出力電力を
設定すること、マイクロコントローラ16により外科医パ
ネル15からの所望レベルの出力電力を受けること、マイ
クロコントローラ16により所望レベルの出力電力に基づ
いて電圧閾値を設定すること、可調整の波形発生器14に
より無線周波波形を発生すること、可調整の波形発生器
14により波形の周波数を調整すること、可調整の波形発
生器14に電気的に接続された無線周波出力段17により無
線周波波形を受けること、無線周波出力段17により患者
回路11への伝送のための出力電圧及び出力電流を発生す
ること、無線周波出力段17に接続された電圧センサ18に
より出力電圧を受けること、電圧センサ18により出力電
圧に比例した第１信号を発生すること、無線周波出力段
17に接続された電流センサ20により出力電流を受けるこ
と、電流センサ20により出力電流に比例した第２信号を
発生すること、電圧及び電流センサ20に電気的に接続さ
れたインピーダンス測定回路により第１信号及び第２信
号を受けること、インピーダンス測定回路により患者回
路11における負荷のインピーダンスを計算すること、火
花制御回路19により電気的にマイクロコントローラ16か
らの電圧閾値を受けること、火花制御回路19により電圧
センサ18からの第１信号を受けること、並びに負荷のイ
ンピーダンスが一般的に約4096オームより小さく且つ第
１信号が電圧閾値より大きいときの条件に応答して波形
の周波数を調整すること、が含まれている。

Claims (6)

    (57)【特許請求の範囲】
  1. 【請求項１】患者回路11における射出火花発生を抑制す
    る射出火花制御システムを備えた電気外科用ゼネレータ
    10であって、 無線周波波形を発生するための且つ前記波形の周波数を
    調整することのできる、電気外科用ゼネレータ10におけ
    る可調整の波形発生器14と、 無線周波波形を受けるために並びに患者回路11に伝送可
    能な出力電圧及び出力電流を発生するために、可調整の
    波形発生器14に電気的に接続された無線周波出力段17
    と、 前記出力電圧を受けるために無線周波出力段17に接続さ
    れていて、前記出力電圧に比例した第１信号を発生する
    ことのできる電圧センサ18と、 前記第１信号を受けるために電圧センサ18に電気的に接
    続された火花制御回路19であって、可調整の波形発生器
    14に電気的に接続されていて、波形発生器14により、前
    記第１信号に応答して前記波形の周波数を一時的に停止
    させ、次に一時的にそれを部分的に調整させて、調整さ
    れた周波数が無線周波出力段17における利得の低下を生
    じさせるようにする火花制御回路19と、 を含んでいる電気外科用ゼネレータ10。
  2. 【請求項２】火花制御回路19が更に、 前記出力電流を受けるために無線周波出力段17に接続さ
    れていて、前記出力電流に比例した第２信号を発生する
    ことのできる電流センサ20と、 前記第１信号及び前記第２信号を受けるために並びに患
    者11における負荷のインピーダンスを計算するために電
    気的に接続されたインピーダンス測定装置21と、 を含んでいる、請求項１の電気外科用ゼネレータ10。
  3. 【請求項３】インピーダンス測定装置21から負荷のイン
    ピーダンスを受けるように電気的に接続された入力と、
    火花制御回路19を可能化するために可調整の波形発生器
    14に電気的に接続された出力と、を有するマイクロコン
    トローラ16を更に含んでいる、請求項２の電気外科用ゼ
    ネレータ10。
  4. 【請求項４】５ミリ秒ないし200ミリ秒の範囲にある時
    間の間、出力段17を遮断するための、マイクロコントロ
    ーラ16におけるアルゴリズムを更に含んでいる、請求項
    ３の電気外科用ゼネレータ10。
  5. 【請求項５】火花制御回路19が更に、 電圧センサ18から前記第１信号を受けるように且つ前記
    第１信号からのピーク値を保持するために接続されてい
    るピーク検出器と、 前記ピーク検出器から前記ピーク値を受けるように接続
    され且つ電圧閾値を受けるように接続されていて、前記
    ピーク値が前記電圧閾値を越えたときには常に高信号を
    発生する比較器と、 前記比較器から前記高信号を受けるように接続されたワ
    ンショットであって、可調整の波形発生器14に電気的に
    接続された出力を備えており、前記高信号が前記比較器
    から受信されたときには常にこの出力にパルスを発生す
    るように設定された前記ワンショット、 を含んでいる、請求項１の電気外科用ゼネレータ10。
  6. 【請求項６】外科医により使用されたときに患者回路11
    による患者13に対する射出火花発生を抑制する射出火花
    制御システムを備えた電気外科用ゼネレータ10であっ
    て、 所望レベルの出力電力を設定するために、外科医が操作
    できる、電気外科用ゼネレータ10における外科医パネル
    15と、 外科医パネル15から所望レベルの出力電力を受けるよう
    に電気的に接続されていて、前記所望レベルの出力電力
    に基づいて電圧閾値を設定することのできる、電気外科
    用ゼネレータ10におけるマイクロコントローラ16と、 無線周波波形を発生するための及び前記波形の周波数を
    調整するための、電気外科用ゼネレータ10における可調
    整の波形発生器14と、 前記無線周波波形を受けるために並びに患者回路11に伝
    送可能な出力電圧及び出力電流を発生するために、可調
    整の波形発生器14に電気的に接続された無線周波出力段
    17と、 前記出力電圧を受けるために無線周波出力段17に接続さ
    れていて、出力電圧に比例した第１信号を発生すること
    のできる電圧センサ18と、 マイクロプロセッサ16から電圧閾値を受けるためにマイ
    クロプロセッサ16に電気的に接続され、且つ前記第１信
    号を受けるために電圧センサ18に電気的に接続された火
    花制御回路19であって、前記第１信号が前記電圧閾値よ
    り大きいときに応答して、前記波形の周波数を一時的に
    停止し、次に一時的にこれを部分的に調整して、これに
    より調整された周波数が無線周波出力段17における利得
    及び効率の低下を生じさせるようにするために、可調整
    の波形発生器14に電気的に接続されている火花制御回路
    19、 を含んでいる電気外科用ゼネレータ10。
JP9500259A 1995-06-06 1996-06-03 電気外科用ゼネレータのための射出火花制御 Expired - Fee Related JP2960971B2 (ja)

Applications Claiming Priority (4)

Application Number Priority Date Filing Date Title
US08/479,424 US5628745A (en) 1995-06-06 1995-06-06 Exit spark control for an electrosurgical generator
US08/479,424 1995-06-06
US479,424 1995-06-06
PCT/IB1996/000550 WO1996039087A1 (en) 1995-06-06 1996-06-03 Exit spark control for an electrosurgical generator

Publications (2)

Publication Number Publication Date
JPH10507394A JPH10507394A (ja) 1998-07-21
JP2960971B2 true JP2960971B2 (ja) 1999-10-12

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EP (1) EP0833592B1 (ja)
JP (1) JP2960971B2 (ja)
AT (1) ATE192310T1 (ja)
AU (1) AU714068B2 (ja)
CA (1) CA2221285C (ja)
DE (1) DE69608104T2 (ja)
ES (1) ES2148763T3 (ja)
WO (1) WO1996039087A1 (ja)

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CA2221285C (en) 2001-08-14
EP0833592B1 (en) 2000-05-03
DE69608104D1 (de) 2000-06-08
ATE192310T1 (de) 2000-05-15
ES2148763T3 (es) 2000-10-16
AU714068B2 (en) 1999-12-16
AU5700896A (en) 1996-12-24
JPH10507394A (ja) 1998-07-21
CA2221285A1 (en) 1996-12-12
EP0833592A1 (en) 1998-04-08
MX9709425A (es) 1998-07-31
US5628745A (en) 1997-05-13
DE69608104T2 (de) 2001-02-01
WO1996039087A1 (en) 1996-12-12

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