JP2000350732A - 電気外科手術システム、電気外科手術用ジェネレータ、および電気外科手術で組織を切断または切除するための方法 - Google Patents
電気外科手術システム、電気外科手術用ジェネレータ、および電気外科手術で組織を切断または切除するための方法Info
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- 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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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
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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
- 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
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- A61B18/1233—Generators therefor with circuits for assuring patient safety
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Abstract
(57)【要約】
【課題】 高周波ジェネレータと処置電極を備える器具
とを有する電気外科手術システムにおいて、電極からの
熱電子放出を感知するための回路を高周波電力の電極へ
の供給を制御する手段として含む、ジェネレータ（１
０）を提供する。 【解決手段】 熱電子放出は、分離された出力を有する
検出器を用いてジェネレータ（１０）の出力における直
流電圧を検出することによって感知され、ジェネレータ
の出力は直流電圧を予め定められたしきい値に制限する
ように制御される。したがって、電極（３０，３６）の
温度は電極破壊を回避するように制限され得る。本発明
は、電気外科手術の処置によって生じる神経の刺激を減
じるためにも有効である。
とを有する電気外科手術システムにおいて、電極からの
熱電子放出を感知するための回路を高周波電力の電極へ
の供給を制御する手段として含む、ジェネレータ（１
０）を提供する。 【解決手段】 熱電子放出は、分離された出力を有する
検出器を用いてジェネレータ（１０）の出力における直
流電圧を検出することによって感知され、ジェネレータ
の出力は直流電圧を予め定められたしきい値に制限する
ように制御される。したがって、電極（３０，３６）の
温度は電極破壊を回避するように制限され得る。本発明
は、電気外科手術の処置によって生じる神経の刺激を減
じるためにも有効である。
Description
【０００１】
【発明の属する技術分野】本発明は、電気外科手術シス
テム、電気外科手術用器具、および電気外科手術を行な
うための方法に関する。
テム、電気外科手術用器具、および電気外科手術を行な
うための方法に関する。
【０００２】
【従来の技術】高周波電圧が供給される１つ以上の活動
電極を備える先端を有する器具を用いて電気外科的な組
織を切断または除去することは、通常、活動電極と処置
中の組織との間、または水中電気外科手術の場合は活動
電極と処置中の組織を覆っている導電性の液体との間に
生じるアークにより、細胞の裂傷を伴う。ＥＰ−Ａ−０
７５４４３７号に記載のように、電極を燃焼または溶融
させるのに十分な高周波電力が電極に供給されると電極
の破壊が起こり得るが、これは、電極のピーク電圧を感
知し、かつフィードバックを与えて印加電力を減じるこ
とにより最大ピーク電圧を設定することによって回避で
きる。所与の電力設定に関して、電極の温度は、熱が放
散され得る速度に依存し、この速度は、組織の係わり程
度、電極構造、および電極まわりの流体フローなどの変
数に依存する、ということがわかるであろう。結果とし
て、電極の破壊を回避するためには、最悪の放散状態
（すなわち冷却液がなく、かつ／または組織が電極を取
り囲んでいる場合）における損傷を防ぐように、ピーク
電圧の限界を十分低いレベルに設定しなければならな
い。
電極を備える先端を有する器具を用いて電気外科的な組
織を切断または除去することは、通常、活動電極と処置
中の組織との間、または水中電気外科手術の場合は活動
電極と処置中の組織を覆っている導電性の液体との間に
生じるアークにより、細胞の裂傷を伴う。ＥＰ−Ａ−０
７５４４３７号に記載のように、電極を燃焼または溶融
させるのに十分な高周波電力が電極に供給されると電極
の破壊が起こり得るが、これは、電極のピーク電圧を感
知し、かつフィードバックを与えて印加電力を減じるこ
とにより最大ピーク電圧を設定することによって回避で
きる。所与の電力設定に関して、電極の温度は、熱が放
散され得る速度に依存し、この速度は、組織の係わり程
度、電極構造、および電極まわりの流体フローなどの変
数に依存する、ということがわかるであろう。結果とし
て、電極の破壊を回避するためには、最悪の放散状態
（すなわち冷却液がなく、かつ／または組織が電極を取
り囲んでいる場合）における損傷を防ぐように、ピーク
電圧の限界を十分低いレベルに設定しなければならな
い。
【０００３】電極におけるアーク放電が神経刺激を引き
起こし得ることは公知である。これは、電極が加熱され
るときの熱電子効果によるものである。ジェネレータの
高周波源と電極との間に結合キャパシタを用いることは
不可欠であるので、電極は分離され、キャパシタ上に電
荷を構築することが可能になり、これにより、電極が組
織または組織を覆う導電性の流体に触れると神経刺激が
起こる。
起こし得ることは公知である。これは、電極が加熱され
るときの熱電子効果によるものである。ジェネレータの
高周波源と電極との間に結合キャパシタを用いることは
不可欠であるので、電極は分離され、キャパシタ上に電
荷を構築することが可能になり、これにより、電極が組
織または組織を覆う導電性の流体に触れると神経刺激が
起こる。
【０００４】
【発明の概要】本発明は、熱電子効果が温度依存性であ
り、したがって電極温度の表示として用いられ得るとい
う認識に基づくものである。
り、したがって電極温度の表示として用いられ得るとい
う認識に基づくものである。
【０００５】したがって、本発明は、電気外科手術用器
具の処置電極に供給するための高周波エネルギ源を含む
ジェネレータを含み、このジェネレータは、電極からの
熱電子放出を感知するための回路を含む。
具の処置電極に供給するための高周波エネルギ源を含む
ジェネレータを含み、このジェネレータは、電極からの
熱電子放出を感知するための回路を含む。
【０００６】本発明はまた、高周波エネルギ源を含むジ
ェネレータと、このジェネレータに結合されて、処置電
極を有する電気外科手術用器具とを含む、電気外科手術
システムも含み、このシステムは、処置電極において２
ボルトを超える直流オフセットを検出するように構成さ
れる直流電圧検出器と、この検出器に結合されて、直流
オフセットに応答して器具に与えられる高周波エネルギ
を制御するための制御回路とを含む。この態様で、熱電
子効果による処置電極における直流電圧のレベルは、た
とえば電極温度を制御する手段として、制限され得る。
実際には、熱電子効果のアーク放電（特に、処置電極が
非常に熱くなるようなレベルおよび環境におけるアーク
放電）との関連性が、電極のオーバヒートを保護するた
めに本発明に従って用いられ得る。これにより、最悪の
場合以外の熱放散を有する環境において用いられる電極
を、先行技術の電圧感知技術を用いた場合に可能である
とされるよりも高温で動作させることが可能になり、結
果的に、組織が切断または除去され得る速度が増す。
ェネレータと、このジェネレータに結合されて、処置電
極を有する電気外科手術用器具とを含む、電気外科手術
システムも含み、このシステムは、処置電極において２
ボルトを超える直流オフセットを検出するように構成さ
れる直流電圧検出器と、この検出器に結合されて、直流
オフセットに応答して器具に与えられる高周波エネルギ
を制御するための制御回路とを含む。この態様で、熱電
子効果による処置電極における直流電圧のレベルは、た
とえば電極温度を制御する手段として、制限され得る。
実際には、熱電子効果のアーク放電（特に、処置電極が
非常に熱くなるようなレベルおよび環境におけるアーク
放電）との関連性が、電極のオーバヒートを保護するた
めに本発明に従って用いられ得る。これにより、最悪の
場合以外の熱放散を有する環境において用いられる電極
を、先行技術の電圧感知技術を用いた場合に可能である
とされるよりも高温で動作させることが可能になり、結
果的に、組織が切断または除去され得る速度が増す。
【０００７】典型的には、オーバヒートの保護のために
は、制御回路および検出器は、直流オフセットを５０Ｖ
から１００Ｖの範囲の予め定められた直流電圧レベルに
制限するように動作可能である。実際には、実際の電圧
レベルは電極の構成および電極の材料に依存する。した
がって、白金の電極を用いると、電圧の限界は電極電圧
が１６００℃（白金の融点）に近くなると生じる限界と
同じものに設定される。
は、制御回路および検出器は、直流オフセットを５０Ｖ
から１００Ｖの範囲の予め定められた直流電圧レベルに
制限するように動作可能である。実際には、実際の電圧
レベルは電極の構成および電極の材料に依存する。した
がって、白金の電極を用いると、電圧の限界は電極電圧
が１６００℃（白金の融点）に近くなると生じる限界と
同じものに設定される。
【０００８】これに代えて、最大直流オフセット電圧
は、たとえば神経外科（脊椎領域における外科手術）お
よび筋肉組織などの敏感な部位での神経刺激を減じるた
めに、かなり低い値に設定してもよい。
は、たとえば神経外科（脊椎領域における外科手術）お
よび筋肉組織などの敏感な部位での神経刺激を減じるた
めに、かなり低い値に設定してもよい。
【０００９】本発明の好ましい実施例では、ジェネレー
タは処置電極に接続可能な出力端子を有し、検出器は、
（ｉ）出力端子に接続される検出入力と（ｉｉ）検出器
を制御回路に接続するアイソレーション装置とを有す
る。検出器は、ジェネレータ出力端子に結合された電源
回路を有することにより、かつ出力端子に与えられた高
周波電気外科手術信号を整流するための整流器を含むこ
とにより、ジェネレータの高周波出力エネルギから電力
を与えられ得る。これは、高周波出力電圧がアーク放電
と一致するレベルに到達するまで起こらないので可能で
ある。検出器がより低い電圧では機能しないという事実
は、結果的に不利にはならない。典型的には、検出器の
出力でアイソレーションを達成するために、それは直流
オフセットを表わす交互に変わる測定信号を発生する発
振器とを含み、アイソレーション装置は、交互に変わる
測定信号を受け、かつそれを制御回路へ送るように結合
されたオプトアイソレータを含む。好ましい検出器はま
た、たとえば導電性の流体フィールドにおいてバイポー
ラ電極アセンブリを使用する際に流体の欠如が直流の極
性を反転させると高周波源を使用不能にするために用い
られ得る、故障状態インジケータとしての逆極性直流オ
フセット検出器も含む。
タは処置電極に接続可能な出力端子を有し、検出器は、
（ｉ）出力端子に接続される検出入力と（ｉｉ）検出器
を制御回路に接続するアイソレーション装置とを有す
る。検出器は、ジェネレータ出力端子に結合された電源
回路を有することにより、かつ出力端子に与えられた高
周波電気外科手術信号を整流するための整流器を含むこ
とにより、ジェネレータの高周波出力エネルギから電力
を与えられ得る。これは、高周波出力電圧がアーク放電
と一致するレベルに到達するまで起こらないので可能で
ある。検出器がより低い電圧では機能しないという事実
は、結果的に不利にはならない。典型的には、検出器の
出力でアイソレーションを達成するために、それは直流
オフセットを表わす交互に変わる測定信号を発生する発
振器とを含み、アイソレーション装置は、交互に変わる
測定信号を受け、かつそれを制御回路へ送るように結合
されたオプトアイソレータを含む。好ましい検出器はま
た、たとえば導電性の流体フィールドにおいてバイポー
ラ電極アセンブリを使用する際に流体の欠如が直流の極
性を反転させると高周波源を使用不能にするために用い
られ得る、故障状態インジケータとしての逆極性直流オ
フセット検出器も含む。
【００１０】本発明の第２の局面に従うと、高周波エネ
ルギ源と、活動出力端子と、リターン出力端子と、エネ
ルギ源と活動出力端子との間に直流分離キャパシタとを
含む電気外科手術用ジェネレータは、２ボルトを超える
直流電圧を検出するための分離キャパシタの出力端子側
に接続された分路入力と、分路入力における直流オフセ
ット電圧に応答して活動出力端子に与えられた高周波エ
ネルギを制御するためにエネルギ源に結合された制御回
路とを有する、直流オフセット検出器を有する。
ルギ源と、活動出力端子と、リターン出力端子と、エネ
ルギ源と活動出力端子との間に直流分離キャパシタとを
含む電気外科手術用ジェネレータは、２ボルトを超える
直流電圧を検出するための分離キャパシタの出力端子側
に接続された分路入力と、分路入力における直流オフセ
ット電圧に応答して活動出力端子に与えられた高周波エ
ネルギを制御するためにエネルギ源に結合された制御回
路とを有する、直流オフセット検出器を有する。
【００１１】本発明の第３の局面に従って、電気外科手
術で組織を切断または切除するための方法は、電気外科
手術用器具に高周波エネルギを与えることによりその器
具の処置電極におけるアーク放電を促進するステップ
と、電極からの熱電子放出によって電極で得られた直流
電圧に従って与えられたエネルギのレベルを調節するス
テップとを含む。高周波エネルギは、電極に実質的な損
傷を与えることなく電極の温度を最大にするように調節
することができ、これは典型的には直流電圧を１００Ｖ
未満のしきい値に制限することによって行なわれる。
術で組織を切断または切除するための方法は、電気外科
手術用器具に高周波エネルギを与えることによりその器
具の処置電極におけるアーク放電を促進するステップ
と、電極からの熱電子放出によって電極で得られた直流
電圧に従って与えられたエネルギのレベルを調節するス
テップとを含む。高周波エネルギは、電極に実質的な損
傷を与えることなく電極の温度を最大にするように調節
することができ、これは典型的には直流電圧を１００Ｖ
未満のしきい値に制限することによって行なわれる。
【００１２】上記の好ましい実施例では、熱電子効果の
検出は、ジェネレータの出力ステージにおいてキャパシ
タが高い値の抵抗を介して放電し続けることによって生
じ、この電極にわたって検出されたＤＣ電圧が、この効
果を表わすものとなる。この検出技術は、出力ステージ
におけるキャパシタの放電に対する時定数によって制限
されるので、これは応答時間が比較的遅いという欠点を
有する。この時定数は、回路内の容量と抵抗との積であ
る。キャパシタは、出力インピーダンスを減じるために
必然的に大きくなり、出力端子にわたって接続される分
路抵抗は、強い直流が患者に流れないように大きくされ
ている。
検出は、ジェネレータの出力ステージにおいてキャパシ
タが高い値の抵抗を介して放電し続けることによって生
じ、この電極にわたって検出されたＤＣ電圧が、この効
果を表わすものとなる。この検出技術は、出力ステージ
におけるキャパシタの放電に対する時定数によって制限
されるので、これは応答時間が比較的遅いという欠点を
有する。この時定数は、回路内の容量と抵抗との積であ
る。キャパシタは、出力インピーダンスを減じるために
必然的に大きくなり、出力端子にわたって接続される分
路抵抗は、強い直流が患者に流れないように大きくされ
ている。
【００１３】さらなる実施例は、熱電子放出によって影
響を受ける交流現象が検出される活動端子からの熱電子
放出を検出するための代替的な技術を提供し、ジェネレ
ータの出力端子にわたるＤＣ導電経路の必要性をなく
す。したがって、本発明のさらなる局面は、変調ジェネ
レータ出力と、ＤＣ導電経路を全く含まない結合によっ
てジェネレータの出力に結合される検出回路とを提供
し、この検出回路は、ジェネレータの出力の変調周波数
に同調されており、活動電極からの熱電子放出により、
検出回路のジェネレータ出力における変調が不可欠なも
のとなる。
響を受ける交流現象が検出される活動端子からの熱電子
放出を検出するための代替的な技術を提供し、ジェネレ
ータの出力端子にわたるＤＣ導電経路の必要性をなく
す。したがって、本発明のさらなる局面は、変調ジェネ
レータ出力と、ＤＣ導電経路を全く含まない結合によっ
てジェネレータの出力に結合される検出回路とを提供
し、この検出回路は、ジェネレータの出力の変調周波数
に同調されており、活動電極からの熱電子放出により、
検出回路のジェネレータ出力における変調が不可欠なも
のとなる。
【００１４】好ましい実施例では、ジェネレータ出力の
振幅は、熱電子効果が存在しない場合、ジェネレータ出
力の単一サイクルにわたって測定されたジェネレータ出
力の平均値が一定に保たれるような態様で変調され、熱
電子放出が存在する場合、単一サイクルにわたって測定
されたジェネレータ出力の平均値はジェネレータの振幅
変調の周波数で変化し、この平均値における変化の振幅
は熱電子効果の程度に対応する。この検出回路は、適切
に同調された共振回路、およびジェネレータの出力ステ
ージに帰納的に結合されて熱電子効果により生じる共振
回路内の電圧を検出する検出器によってもたらされ得
る。
振幅は、熱電子効果が存在しない場合、ジェネレータ出
力の単一サイクルにわたって測定されたジェネレータ出
力の平均値が一定に保たれるような態様で変調され、熱
電子放出が存在する場合、単一サイクルにわたって測定
されたジェネレータ出力の平均値はジェネレータの振幅
変調の周波数で変化し、この平均値における変化の振幅
は熱電子効果の程度に対応する。この検出回路は、適切
に同調された共振回路、およびジェネレータの出力ステ
ージに帰納的に結合されて熱電子効果により生じる共振
回路内の電圧を検出する検出器によってもたらされ得
る。
【００１５】ここで、例示のために図面を参照して本発
明を説明する。
明を説明する。
【００１６】
【発明の実施の形態】本発明は、水分を含む場および乾
燥した場の両方における電気外科手術に適用可能であ
る。図１を参照して、このシステムは、接続コード１４
を介してハンドピース１２の形態の電気外科手術用器具
に高周波出力を与える出力ソケット１０Ｓを有する、ジ
ェネレータ１０を含む。ジェネレータは、ハンドピース
１２からコード１４の制御接続を介して、または図示す
るようにフットスイッチ接続コード１８によってジェネ
レータ１０の後部に分離可能に接続されたフットスイッ
チユニット１６を用いて、作動され得る。図示した実施
例では、フットスイッチユニット１６は、ジェネレータ
のそれぞれ脱水モードおよび気化モードを選択するため
の２つのフットスイッチ１６Ａおよび１６Ｂを有する。
ジェネレータのフロントパネルにはそれぞれ脱水および
気化の電力レベルを設定するためのプッシュボタン２０
および２２があり、電力レベルはディスプレイ２４に示
される。モード選択の代替手段としてプッシュボタン２
６が設けられる。
燥した場の両方における電気外科手術に適用可能であ
る。図１を参照して、このシステムは、接続コード１４
を介してハンドピース１２の形態の電気外科手術用器具
に高周波出力を与える出力ソケット１０Ｓを有する、ジ
ェネレータ１０を含む。ジェネレータは、ハンドピース
１２からコード１４の制御接続を介して、または図示す
るようにフットスイッチ接続コード１８によってジェネ
レータ１０の後部に分離可能に接続されたフットスイッ
チユニット１６を用いて、作動され得る。図示した実施
例では、フットスイッチユニット１６は、ジェネレータ
のそれぞれ脱水モードおよび気化モードを選択するため
の２つのフットスイッチ１６Ａおよび１６Ｂを有する。
ジェネレータのフロントパネルにはそれぞれ脱水および
気化の電力レベルを設定するためのプッシュボタン２０
および２２があり、電力レベルはディスプレイ２４に示
される。モード選択の代替手段としてプッシュボタン２
６が設けられる。
【００１７】ハンドピース１２は、図２の部分図に示す
ように、二重電極構造を有する着脱可能な電極アセンブ
リ２８を装着する。
ように、二重電極構造を有する着脱可能な電極アセンブ
リ２８を装着する。
【００１８】図２は、電極アセンブリ２８の末端の拡大
図である。このアセンブリは末端に活動電極３０を有
し、これはこの実施例では、中心の導体３２に接続され
るコイル状に巻かれたワイヤとして形成される。このコ
イル状ワイヤは白金から作製され得る。活動電極３０の
近傍にリターン電極３６が位置付けられ、それは長手お
よび軸方向に延びるセラミックの絶縁体３４によって活
動電極から分離されている。リターン電極３６は、管状
のシャフト４０としてアセンブリ２８（図１参照）の近
接端（ハンドピース１２内でアセンブリが接続コード１
４内の導体に接続されるところ）に延びるスリーブとし
て、内部導体３２のまわりに同軸上に配置される。同様
に、内部導体３２はハンドピース１２に延び、コード１
４内の別の導体に接続される。内部導体３２とリターン
電極３６との間には、リターン電極の内部に延びてリタ
ーン電極３６から活動電極３０の内部伸張部（図示せ
ず）を絶縁するスリーブとして構築された絶縁体３４に
よって絶縁がもたらされる。リターン電極よりも活動電
極においてより大きな電力密度を促進するために、リタ
ーン電極の表面領域は活動電極のものよりかなり大きく
される。電極アセンブリの末端における典型的な寸法に
関しては、リターン電極の直径は典型的には１ｍｍから
３ｍｍの領域であり、リターン電極の露出部分の長手方
向の伸張は典型的には１ｍｍから５ｍｍの間であり、活
動電極からの長手方向の間隔は１ｍｍから５ｍｍの間で
ある。電極アセンブリ２８は、シャフト４０を覆いセラ
ミックの絶縁体３４の近傍で終結する絶縁シース４２を
有し、シャフト４０の末端をリターン電極３６として露
出したままにする。
図である。このアセンブリは末端に活動電極３０を有
し、これはこの実施例では、中心の導体３２に接続され
るコイル状に巻かれたワイヤとして形成される。このコ
イル状ワイヤは白金から作製され得る。活動電極３０の
近傍にリターン電極３６が位置付けられ、それは長手お
よび軸方向に延びるセラミックの絶縁体３４によって活
動電極から分離されている。リターン電極３６は、管状
のシャフト４０としてアセンブリ２８（図１参照）の近
接端（ハンドピース１２内でアセンブリが接続コード１
４内の導体に接続されるところ）に延びるスリーブとし
て、内部導体３２のまわりに同軸上に配置される。同様
に、内部導体３２はハンドピース１２に延び、コード１
４内の別の導体に接続される。内部導体３２とリターン
電極３６との間には、リターン電極の内部に延びてリタ
ーン電極３６から活動電極３０の内部伸張部（図示せ
ず）を絶縁するスリーブとして構築された絶縁体３４に
よって絶縁がもたらされる。リターン電極よりも活動電
極においてより大きな電力密度を促進するために、リタ
ーン電極の表面領域は活動電極のものよりかなり大きく
される。電極アセンブリの末端における典型的な寸法に
関しては、リターン電極の直径は典型的には１ｍｍから
３ｍｍの領域であり、リターン電極の露出部分の長手方
向の伸張は典型的には１ｍｍから５ｍｍの間であり、活
動電極からの長手方向の間隔は１ｍｍから５ｍｍの間で
ある。電極アセンブリ２８は、シャフト４０を覆いセラ
ミックの絶縁体３４の近傍で終結する絶縁シース４２を
有し、シャフト４０の末端をリターン電極３６として露
出したままにする。
【００１９】動作にあたっては、導電性の流体フィール
ドで組織の切断または除去を行なうための器具として、
図２に示すように、処置すべき組織４４に電極アセンブ
リ２８が与えられ、手術部位は、活動電極３０とリター
ン電極３６との両方を浸漬する通常の食塩水（０．９％
ｗ／ｖ）の溶液４６に浸漬される。
ドで組織の切断または除去を行なうための器具として、
図２に示すように、処置すべき組織４４に電極アセンブ
リ２８が与えられ、手術部位は、活動電極３０とリター
ン電極３６との両方を浸漬する通常の食塩水（０．９％
ｗ／ｖ）の溶液４６に浸漬される。
【００２０】電極アセンブリは、一方の電極（活動電極
３０）のみがユニットの末端に軸方向に延びる、バイポ
ーラであるのが効果的である。つまり、リターン電極
は、水分を含む場における通常の状況では処置中の組織
から間隔を保って位置付けられ、組織とリターン電極と
の間にはリターン電極と接触する導電性の液体を介して
電流経路が存在する。導電性の液体４６は、バイポーラ
電気外科手術エネルギの伝達に関するかぎり、組織の低
インピーダンス伸張としてみなされ得る。
３０）のみがユニットの末端に軸方向に延びる、バイポ
ーラであるのが効果的である。つまり、リターン電極
は、水分を含む場における通常の状況では処置中の組織
から間隔を保って位置付けられ、組織とリターン電極と
の間にはリターン電極と接触する導電性の液体を介して
電流経路が存在する。導電性の液体４６は、バイポーラ
電気外科手術エネルギの伝達に関するかぎり、組織の低
インピーダンス伸張としてみなされ得る。
【００２１】電極３０と電極３６との間に十分な高周波
電圧が与えられると、導電性の液体４６中での電力の放
散により液体は気化し、最初に活動電極３０の表面上に
小さな気泡を形成し、これが最終的には、電極が蒸気ポ
ケット５０に完全に包囲されるまで凝集する。蒸気ポケ
ット５０は、活動電極３０と蒸気−食塩水界面との間の
蒸気ポケットにわたる放電５２によって支持される。電
力放散の大部分が、ここでは活動電極の結果的に生じた
熱とともにこのポケット内で起こり、放散されるエネル
ギの量は伝えられる電力の関数である。図２に示すよう
に、活動電極３０を組織４４の表面近傍に保持して蒸気
ポケットが組織表面を遮るようにすることにより、電極
と組織との間に生じるアーク放電による細胞の裂傷によ
って組織が除去される。
電圧が与えられると、導電性の液体４６中での電力の放
散により液体は気化し、最初に活動電極３０の表面上に
小さな気泡を形成し、これが最終的には、電極が蒸気ポ
ケット５０に完全に包囲されるまで凝集する。蒸気ポケ
ット５０は、活動電極３０と蒸気−食塩水界面との間の
蒸気ポケットにわたる放電５２によって支持される。電
力放散の大部分が、ここでは活動電極の結果的に生じた
熱とともにこのポケット内で起こり、放散されるエネル
ギの量は伝えられる電力の関数である。図２に示すよう
に、活動電極３０を組織４４の表面近傍に保持して蒸気
ポケットが組織表面を遮るようにすることにより、電極
と組織との間に生じるアーク放電による細胞の裂傷によ
って組織が除去される。
【００２２】この動作モードは比較的広範囲の電力レベ
ルにわたって維持され得るが、伝えられる電力をこの範
囲を超えて増加させると、電極の温度が急速に上昇し、
電極に損傷を与える可能性がある。これが起こる点は、
熱が電極から取り除かれる速度に依存し、この速度は、
電極３０、電極３０が組織に近接しているところ、およ
び最悪の場合は電極３０が組織に埋まったところを通過
する流体のフロー４６による対流の影響を受けるという
ことがわかるであろう。したがって、ピーク電圧が電極
における無制御の温度上昇を防ぐように確立され得る一
方、このような限界は、効を奏するためには、最悪の場
合の熱放散状態におけるそのような上昇を防ぐとされる
レベルに設定されなければならない。
ルにわたって維持され得るが、伝えられる電力をこの範
囲を超えて増加させると、電極の温度が急速に上昇し、
電極に損傷を与える可能性がある。これが起こる点は、
熱が電極から取り除かれる速度に依存し、この速度は、
電極３０、電極３０が組織に近接しているところ、およ
び最悪の場合は電極３０が組織に埋まったところを通過
する流体のフロー４６による対流の影響を受けるという
ことがわかるであろう。したがって、ピーク電圧が電極
における無制御の温度上昇を防ぐように確立され得る一
方、このような限界は、効を奏するためには、最悪の場
合の熱放散状態におけるそのような上昇を防ぐとされる
レベルに設定されなければならない。
【００２３】本発明に従って、電極への高周波電力の伝
達は電極の温度を感知することによって制御される。こ
れは、以下に図３のＡおよびＢを参照して説明するよう
に、熱電子効果を監視することにより間接的に行なわれ
る。
達は電極の温度を感知することによって制御される。こ
れは、以下に図３のＡおよびＢを参照して説明するよう
に、熱電子効果を監視することにより間接的に行なわれ
る。
【００２４】図３Ａを参照して、本発明に従ったシステ
ムは、電気外科手術用器具の活動電極およびリターン電
極がそれぞれ接続される第１の出力端子６４と第２の出
力端子６６との間に結合キャパシタ６２および６３を介
して電気外科手術電圧を伝達する、高周波電圧源６０を
含む。図２に示すように、活動電極においてアーク放電
が起こると、電極の温度に依存して、組織４４から間隔
をあけて電極を位置付けている間に電極から熱電子放出
が起こり、これが活動出力端子６４に正の電位を構築す
ることにつながる。実際には、加熱された活動電極３
０、組織、導電性の流体、およびリターン電極はともに
整流器として動作し、導電性の溶液はアノードとして、
また活動電極は整流器のカソードとしてそれぞれ作用す
る。活動電極がより熱くなると、整流はより大きくな
り、またジェネレータの出力端子６４における直流オフ
セット電圧もより大きくなる。
ムは、電気外科手術用器具の活動電極およびリターン電
極がそれぞれ接続される第１の出力端子６４と第２の出
力端子６６との間に結合キャパシタ６２および６３を介
して電気外科手術電圧を伝達する、高周波電圧源６０を
含む。図２に示すように、活動電極においてアーク放電
が起こると、電極の温度に依存して、組織４４から間隔
をあけて電極を位置付けている間に電極から熱電子放出
が起こり、これが活動出力端子６４に正の電位を構築す
ることにつながる。実際には、加熱された活動電極３
０、組織、導電性の流体、およびリターン電極はともに
整流器として動作し、導電性の溶液はアノードとして、
また活動電極は整流器のカソードとしてそれぞれ作用す
る。活動電極がより熱くなると、整流はより大きくな
り、またジェネレータの出力端子６４における直流オフ
セット電圧もより大きくなる。
【００２５】温度依存性の正の電位（直流オフセット電
圧）は、出力端子６４に結合された直列高周波チョーク
６８を備える入力回路と、リターン端子６６に接続され
た共通レール７１に結合された平滑キャパシタ７０とを
有する、検出器を用いて監視される。活動出力端子６４
における電圧の直流成分は、したがって、チョーク６８
と平滑キャパシタ７０との接合において累積され、ここ
でその成分は少なくとも２ＭΩであり、典型的には５０
ＭΩから１００ＭΩの間の入力抵抗を提示する電位分割
器７２および７４に与えられる。電位分割器７２および
７４の出力は高インピーダンスバッファ７６に与えら
れ、そのバッファの出力は、駆動信号を電圧制御発振器
（ＶＣＯ）７８に与える。５０ＭΩから１００ＭΩの領
域の入力インピーダンスを与えることにより、５０Ｖか
ら１００Ｖの領域における直流オフセットに対する１μ
Ａの領域の検出電流が生じる。検出電流を低く維持する
ことは、目標の組織とリターン電極との間の直流による
神経の刺激が回避されるという利点を有する。
圧）は、出力端子６４に結合された直列高周波チョーク
６８を備える入力回路と、リターン端子６６に接続され
た共通レール７１に結合された平滑キャパシタ７０とを
有する、検出器を用いて監視される。活動出力端子６４
における電圧の直流成分は、したがって、チョーク６８
と平滑キャパシタ７０との接合において累積され、ここ
でその成分は少なくとも２ＭΩであり、典型的には５０
ＭΩから１００ＭΩの間の入力抵抗を提示する電位分割
器７２および７４に与えられる。電位分割器７２および
７４の出力は高インピーダンスバッファ７６に与えら
れ、そのバッファの出力は、駆動信号を電圧制御発振器
（ＶＣＯ）７８に与える。５０ＭΩから１００ＭΩの領
域の入力インピーダンスを与えることにより、５０Ｖか
ら１００Ｖの領域における直流オフセットに対する１μ
Ａの領域の検出電流が生じる。検出電流を低く維持する
ことは、目標の組織とリターン電極との間の直流による
神経の刺激が回避されるという利点を有する。
【００２６】直流オフセット電圧をＶＣＯ７８において
交互に変わる信号に変換することにより、オプトアイソ
レータ８２を介して検出器の出力８０に接続された分離
制御回路（図示せず）にオフセット電圧レベルを示す信
号を伝達することが可能になる。直流オフセットの表示
は、ジェネレータの出力端子と電力生成および制御回路
との間の安全分離障壁にわたってこの態様で通信され
る。この制御回路では、交互に変わる信号を、単安定お
よびローパスフィルタを用いて変換して直流レベルまで
戻すこともでき、またはゲート式カウンタでカウントし
てデジタル形式で搬送してもよい。いずれの場合も、制
御回路は、直流オフセット電圧が予め定められた値（典
型的には５０Ｖから１００Ｖの範囲内）に到達すると、
電源６０の電圧を減じるように構成される。このよう
に、活動電極の最大安全動作温度に対するしきい値直流
オフセット電圧を選択することによって、活動電極に伝
えられる高周波電力は種々の熱放散状態で最大化され得
る。
交互に変わる信号に変換することにより、オプトアイソ
レータ８２を介して検出器の出力８０に接続された分離
制御回路（図示せず）にオフセット電圧レベルを示す信
号を伝達することが可能になる。直流オフセットの表示
は、ジェネレータの出力端子と電力生成および制御回路
との間の安全分離障壁にわたってこの態様で通信され
る。この制御回路では、交互に変わる信号を、単安定お
よびローパスフィルタを用いて変換して直流レベルまで
戻すこともでき、またはゲート式カウンタでカウントし
てデジタル形式で搬送してもよい。いずれの場合も、制
御回路は、直流オフセット電圧が予め定められた値（典
型的には５０Ｖから１００Ｖの範囲内）に到達すると、
電源６０の電圧を減じるように構成される。このよう
に、活動電極の最大安全動作温度に対するしきい値直流
オフセット電圧を選択することによって、活動電極に伝
えられる高周波電力は種々の熱放散状態で最大化され得
る。
【００２７】図２に示すバイポーラ電極アセンブリが不
正確に用いられると、たとえばアセンブリのまわりに十
分な食塩水がない場合などは、リターン電極３６でアー
ク放電が起こってしまう可能性もある。このような状況
においては、直流オフセットの極性は反転するので、活
動端子６４はリターン電極に対して負になる。図３Ａに
示される検出器は、ＶＣＯ７８をバイパスし、かつたと
えばＯＲゲート８６の一方の入力に結合された出力（こ
の他方の入力はＶＣＯ７８からの交互に変わる出力を受
ける）を有する、比較器８４の形態の逆極性検出回路を
含む。比較器８４の他方の入力は負電圧基準に結合され
る。通常、比較器８４の出力は低く、すなわちＶＣＯに
よって発達した交互に変わる信号はＯＲゲート８６を通
過してオプトアイソレータ８２へ伝えられる。しかしな
がら、ジェネレータの出力端子６４における直流オフセ
ット電圧が比較器８４に与えられた負の基準電圧に依存
してある量以上が負に変わると、比較器８４の出力はハ
イになり、ＯＲゲート８６はＶＣＯ７８からの交互に変
わる信号を遮断し、検出器の出力８０から制御回路に与
えられた交互に変わる信号の欠如が、高周波電源６０を
切るための故障表示として用いられ得る。
正確に用いられると、たとえばアセンブリのまわりに十
分な食塩水がない場合などは、リターン電極３６でアー
ク放電が起こってしまう可能性もある。このような状況
においては、直流オフセットの極性は反転するので、活
動端子６４はリターン電極に対して負になる。図３Ａに
示される検出器は、ＶＣＯ７８をバイパスし、かつたと
えばＯＲゲート８６の一方の入力に結合された出力（こ
の他方の入力はＶＣＯ７８からの交互に変わる出力を受
ける）を有する、比較器８４の形態の逆極性検出回路を
含む。比較器８４の他方の入力は負電圧基準に結合され
る。通常、比較器８４の出力は低く、すなわちＶＣＯに
よって発達した交互に変わる信号はＯＲゲート８６を通
過してオプトアイソレータ８２へ伝えられる。しかしな
がら、ジェネレータの出力端子６４における直流オフセ
ット電圧が比較器８４に与えられた負の基準電圧に依存
してある量以上が負に変わると、比較器８４の出力はハ
イになり、ＯＲゲート８６はＶＣＯ７８からの交互に変
わる信号を遮断し、検出器の出力８０から制御回路に与
えられた交互に変わる信号の欠如が、高周波電源６０を
切るための故障表示として用いられ得る。
【００２８】この実施例では、バッファ７６、ＶＣＯ７
８、比較器８４、およびＯＲゲート８６のための電力は
ジェネレータの出力端子６４および６６に伝えられる高
周波電圧自体から引出されるので、さらなる分離障壁の
必要性が回避される。この目的のために適切な電源を図
３Ｂに示す。ジェネレータの出力端子６４と６６との間
に結合された降圧変圧器９０は、ブリッジ整流器９２を
駆動し、平滑キャパシタ９６にわたって電源出力端子に
直流電圧を伝達する。変圧器９０のニ次巻線の中間タッ
プをリターン出力端子６６に接続し、よって検出器の共
通レールに接続することにより、バッファ７６は正およ
び負の直流オフセット電圧に適合できるように両極性の
電源を設けることが可能になる。このように高周波出力
から電力を引出すことにより検出器が低電圧で動作不可
能になるという事実は、全く不利にならない。なぜな
ら、熱電子効果は、ジェネレータの高周波出力電圧が活
動電極のアーク放電と一致するレベルに達するまで制御
刺激は起こらないということに依存するからである。
８、比較器８４、およびＯＲゲート８６のための電力は
ジェネレータの出力端子６４および６６に伝えられる高
周波電圧自体から引出されるので、さらなる分離障壁の
必要性が回避される。この目的のために適切な電源を図
３Ｂに示す。ジェネレータの出力端子６４と６６との間
に結合された降圧変圧器９０は、ブリッジ整流器９２を
駆動し、平滑キャパシタ９６にわたって電源出力端子に
直流電圧を伝達する。変圧器９０のニ次巻線の中間タッ
プをリターン出力端子６６に接続し、よって検出器の共
通レールに接続することにより、バッファ７６は正およ
び負の直流オフセット電圧に適合できるように両極性の
電源を設けることが可能になる。このように高周波出力
から電力を引出すことにより検出器が低電圧で動作不可
能になるという事実は、全く不利にならない。なぜな
ら、熱電子効果は、ジェネレータの高周波出力電圧が活
動電極のアーク放電と一致するレベルに達するまで制御
刺激は起こらないということに依存するからである。
【００２９】次に図４を参照して、活動電極１３０およ
びリターン電極１３６を有する電気外科手術用器具に接
続される本発明に従ったジェネレータ１１０の代替例の
概略図で示される。このジェネレータの出力ステージ
は、ジェネレータ出力端子１６４および１６６を介して
高周波源と電極１３０および１３６との間をＤＣ電流が
通過するのを防ぐ、１対の結合キャパシタ１６２および
１６３を含む。さらに、ジェネレータの出力ステージ
は、それぞれ活動電極１３０およびリターン電極１３６
と直列するインジケータ１６８を含む。
びリターン電極１３６を有する電気外科手術用器具に接
続される本発明に従ったジェネレータ１１０の代替例の
概略図で示される。このジェネレータの出力ステージ
は、ジェネレータ出力端子１６４および１６６を介して
高周波源と電極１３０および１３６との間をＤＣ電流が
通過するのを防ぐ、１対の結合キャパシタ１６２および
１６３を含む。さらに、ジェネレータの出力ステージ
は、それぞれ活動電極１３０およびリターン電極１３６
と直列するインジケータ１６８を含む。
【００３０】図５を参照して、ジェネレータの出力振幅
（すなわち出力端子１６４および１６６におけるピーク
ピーク出力電圧）は変調され、この例では、５００ｋＨ
ｚの出力周波数および２５ｋＨｚの周波数で変調された
振幅を有するジェネレータ出力信号が与えられる。当
然、この他のジェネレータおよび変調周波数も採用する
ことができる。活動電極１３６において熱電子効果が何
ら存在しない場合、ジェネレータの出力電圧はゼロ電圧
線に関して対称となり、すなわち、ジェネレータ出力の
単一の期間にわたって、ゼロの基準電圧に対して正の最
大出力電圧の値の増加は対応する負の最大出力電圧の増
加と一致するので、ジェネレータ出力の単一変調サイク
ルにわたって測定されたジェネレータ出力信号の平均値
は一定となる。
（すなわち出力端子１６４および１６６におけるピーク
ピーク出力電圧）は変調され、この例では、５００ｋＨ
ｚの出力周波数および２５ｋＨｚの周波数で変調された
振幅を有するジェネレータ出力信号が与えられる。当
然、この他のジェネレータおよび変調周波数も採用する
ことができる。活動電極１３６において熱電子効果が何
ら存在しない場合、ジェネレータの出力電圧はゼロ電圧
線に関して対称となり、すなわち、ジェネレータ出力の
単一の期間にわたって、ゼロの基準電圧に対して正の最
大出力電圧の値の増加は対応する負の最大出力電圧の増
加と一致するので、ジェネレータ出力の単一変調サイク
ルにわたって測定されたジェネレータ出力信号の平均値
は一定となる。
【００３１】しかしながら、一旦活動電極で十分な加熱
が起こり活動電極からの電子の熱電子放出が起こると、
活動電極からリターン電極へ正味の電子の流れが生じ
る。したがって、リターン電極（アノードとして作用す
る）から活動電極へ流れる正味の電流フローが生じる
（これは、電流フローの検出が正の電荷のフローとして
規定されるからである）。次に図６を参照して、このよ
うに変調されたジェネレータ出力電圧の波形を一方向
（ここでは正の方向）にシフトさせることによって、単
一サイクルにわたる出力電圧の平均は非線形の態様でゼ
ロボルトで一定になるのではなく、電極における熱電子
効果によりジェネレータ出力は部分的に整流され、単一
サイクルにわたって測定された平均出力電圧はゼロでな
い電圧になる、という効果が得られる。この電圧の大き
さは振幅変調の周波数（この例では２５ｋＨｚ）で変化
する。この平均出力電圧における変化は、図６に線ＶAV
で示される。さらに、この平均出力電圧における変化の
振幅Ａは、ジェネレータの出力における正方向への位相
ずれの程度に依存しており、最大振幅２５ｋＨｚの信号
は振幅変調の深さの２倍になっている。この振幅Ａは、
リターン電極から活動電極への正味電流フロー度の測定
値であり、したがって、活動電極における熱電子効果の
測定値であり、これはまた活動電極温度の測定値でもあ
る。
が起こり活動電極からの電子の熱電子放出が起こると、
活動電極からリターン電極へ正味の電子の流れが生じ
る。したがって、リターン電極（アノードとして作用す
る）から活動電極へ流れる正味の電流フローが生じる
（これは、電流フローの検出が正の電荷のフローとして
規定されるからである）。次に図６を参照して、このよ
うに変調されたジェネレータ出力電圧の波形を一方向
（ここでは正の方向）にシフトさせることによって、単
一サイクルにわたる出力電圧の平均は非線形の態様でゼ
ロボルトで一定になるのではなく、電極における熱電子
効果によりジェネレータ出力は部分的に整流され、単一
サイクルにわたって測定された平均出力電圧はゼロでな
い電圧になる、という効果が得られる。この電圧の大き
さは振幅変調の周波数（この例では２５ｋＨｚ）で変化
する。この平均出力電圧における変化は、図６に線ＶAV
で示される。さらに、この平均出力電圧における変化の
振幅Ａは、ジェネレータの出力における正方向への位相
ずれの程度に依存しており、最大振幅２５ｋＨｚの信号
は振幅変調の深さの２倍になっている。この振幅Ａは、
リターン電極から活動電極への正味電流フロー度の測定
値であり、したがって、活動電極における熱電子効果の
測定値であり、これはまた活動電極温度の測定値でもあ
る。
【００３２】図４を再び参照して、熱電子効果の結果と
して起こる平均出力電圧の２５ｋＨｚの変化を検出する
ために、ジェネレータは、変調周波数（ここでは２５ｋ
Ｈｚ）に同調された共振回路１７２および１７４を有
し、かつ交互に変わる電圧感知ステージ１７６を含む、
感知回路１７０を含む。この共振回路は並列共振回路で
あり、そのインダクタ１７４は出力ステージの直列イン
ダクタ１６８に帰納的に結合され、このインダクタは出
力端子１６４および１６６からのＤＣで感知回路を分離
する分離変圧器を形成する。活動電極１３０に熱電子効
果が全くない場合、ジェネレータ出力への正味２５ｋＨ
ｚの成分は存在しない。なぜなら、基本的なジェネレー
タ出力はジェネレータ動作周波数５００ｋＨｚで正弦波
形であり、その動作周波数での単一サイクルにわたって
測定された平均値はゼロボルトで一定に保たれるからで
ある。熱電子放出が一旦起こると、ジェネレータ出力に
おける正方向の位相ずれは平均ジェネレータ出力に２５
ｋＨｚの成分を導入し、この平均値における２５ｋＨｚ
の変化の大きさはＡＣ電圧感知ステージ１７６で検出さ
れ、その出力は、上述したように、活動電極１３０にお
ける熱電子効果の程度を直接示すものであり、したがっ
て活動電極１３０の温度を示している。
して起こる平均出力電圧の２５ｋＨｚの変化を検出する
ために、ジェネレータは、変調周波数（ここでは２５ｋ
Ｈｚ）に同調された共振回路１７２および１７４を有
し、かつ交互に変わる電圧感知ステージ１７６を含む、
感知回路１７０を含む。この共振回路は並列共振回路で
あり、そのインダクタ１７４は出力ステージの直列イン
ダクタ１６８に帰納的に結合され、このインダクタは出
力端子１６４および１６６からのＤＣで感知回路を分離
する分離変圧器を形成する。活動電極１３０に熱電子効
果が全くない場合、ジェネレータ出力への正味２５ｋＨ
ｚの成分は存在しない。なぜなら、基本的なジェネレー
タ出力はジェネレータ動作周波数５００ｋＨｚで正弦波
形であり、その動作周波数での単一サイクルにわたって
測定された平均値はゼロボルトで一定に保たれるからで
ある。熱電子放出が一旦起こると、ジェネレータ出力に
おける正方向の位相ずれは平均ジェネレータ出力に２５
ｋＨｚの成分を導入し、この平均値における２５ｋＨｚ
の変化の大きさはＡＣ電圧感知ステージ１７６で検出さ
れ、その出力は、上述したように、活動電極１３０にお
ける熱電子効果の程度を直接示すものであり、したがっ
て活動電極１３０の温度を示している。
【００３３】ある変形例（図示せず）では、共振回路
は、たとえばインダクタ１６８およびそれと平行して接
続されるキャパシタを含む直列接続された並列共振回路
として、ジェネレータ出力回路自体に含まれてもよい。
電圧感知ステージは、共振回路にわたって変調電圧を検
出するために、インダクタ１６８を介して共振回路に帰
納的に結合され得る。
は、たとえばインダクタ１６８およびそれと平行して接
続されるキャパシタを含む直列接続された並列共振回路
として、ジェネレータ出力回路自体に含まれてもよい。
電圧感知ステージは、共振回路にわたって変調電圧を検
出するために、インダクタ１６８を介して共振回路に帰
納的に結合され得る。
【００３４】電圧感知ステージ１７６の出力は、活動電
極で所与の予め設定された温度を維持するために、ジェ
ネレータ出力の絶対振幅（すなわち、振幅変調の程度ま
たは深さではなくジェネレータ出力の最大または最小振
幅）を変化させるフィードバック回路（図示せず）に結
合される。
極で所与の予め設定された温度を維持するために、ジェ
ネレータ出力の絶対振幅（すなわち、振幅変調の程度ま
たは深さではなくジェネレータ出力の最大または最小振
幅）を変化させるフィードバック回路（図示せず）に結
合される。
【００３５】理想的には、変調周波数は、活動電極から
の熱電子放出における変化の速度が、単一変調期間また
はサイクルと比較して遅くなるように選択される。２５
ｋＨｚの変調周波数では、変調期間は４０ミリ秒であ
り、これは図３ＡおよびＢを参照して上述した実施例の
ＤＣ結合された検出回路の応答時間よりかなり短い。
の熱電子放出における変化の速度が、単一変調期間また
はサイクルと比較して遅くなるように選択される。２５
ｋＨｚの変調周波数では、変調期間は４０ミリ秒であ
り、これは図３ＡおよびＢを参照して上述した実施例の
ＤＣ結合された検出回路の応答時間よりかなり短い。
【００３６】ジェネレータの出力電圧における変調の深
さ（すなわち振幅または程度）は、検出すべき熱電子放
出の大きさに従って選択されるのが理想的である。ジェ
ネレータ出力における振幅変調の深さが比較的大きけれ
ば、結果として、ジェネレータ出力における小さな位相
ずれまたはオフセットさえも、動作周波数で単一サイク
ルにわたって測定されたジェネレータ出力の平均値にか
なりの変化を生じることになり、よって比較的小さな熱
電子放出も容易に検出できるようになるであろう。実際
には、熱電子効果によって引き起こされた平均電圧のシ
フトは５０Ｖ領域、動作周波数でのピークピーク出力電
圧は典型的には１０００Ｖである。
さ（すなわち振幅または程度）は、検出すべき熱電子放
出の大きさに従って選択されるのが理想的である。ジェ
ネレータ出力における振幅変調の深さが比較的大きけれ
ば、結果として、ジェネレータ出力における小さな位相
ずれまたはオフセットさえも、動作周波数で単一サイク
ルにわたって測定されたジェネレータ出力の平均値にか
なりの変化を生じることになり、よって比較的小さな熱
電子放出も容易に検出できるようになるであろう。実際
には、熱電子効果によって引き起こされた平均電圧のシ
フトは５０Ｖ領域、動作周波数でのピークピーク出力電
圧は典型的には１０００Ｖである。
【００３７】例示されるジェネレータ出力ステージは、
共振周波数が電極１３０および１３６における負荷のイ
ンピーダンスとともに変化する共振回路であると効果的
である。ジェネレータ出力ステージの共振周波数が動作
周波数に対して、振幅変調の深さよりかなり大きく、か
つジェネレータ出力の単一変調サイクルの持続時間と比
べると短い期間にわたって起こる、ジェネレータ出力電
圧の降下が生じる程度までシフトすると、振幅変調は変
化する共振の結果として起こる振幅における比較的大き
な変化によってかなり変化する。上述のように、熱電子
放出の所与のレベルについて交流電圧計ステージ１７６
によって検出された電圧の大きさは、ジェネレータ出力
の変調の深さの関数であるので、出力ステージの共振に
おける変化が引き起こしたそのような変調の深さにおけ
る変化に有効に関連しないものにより、電圧計１７６に
よる熱電子放出の測定において不正確さが生じる。言い
換えれば、単一サイクルにわたって測定されたジェネレ
ータ出力の平均値における変化が熱電子放出の存在を表
わすとされていても、このような変化の大きさがそのよ
うな放出の程度を表わすとは限らない。なぜなら、ジェ
ネレータの出力ステージで変化する共振の結果として変
調の深さにおける変化が生じる可能性もあるからであ
る。
共振周波数が電極１３０および１３６における負荷のイ
ンピーダンスとともに変化する共振回路であると効果的
である。ジェネレータ出力ステージの共振周波数が動作
周波数に対して、振幅変調の深さよりかなり大きく、か
つジェネレータ出力の単一変調サイクルの持続時間と比
べると短い期間にわたって起こる、ジェネレータ出力電
圧の降下が生じる程度までシフトすると、振幅変調は変
化する共振の結果として起こる振幅における比較的大き
な変化によってかなり変化する。上述のように、熱電子
放出の所与のレベルについて交流電圧計ステージ１７６
によって検出された電圧の大きさは、ジェネレータ出力
の変調の深さの関数であるので、出力ステージの共振に
おける変化が引き起こしたそのような変調の深さにおけ
る変化に有効に関連しないものにより、電圧計１７６に
よる熱電子放出の測定において不正確さが生じる。言い
換えれば、単一サイクルにわたって測定されたジェネレ
ータ出力の平均値における変化が熱電子放出の存在を表
わすとされていても、このような変化の大きさがそのよ
うな放出の程度を表わすとは限らない。なぜなら、ジェ
ネレータの出力ステージで変化する共振の結果として変
調の深さにおける変化が生じる可能性もあるからであ
る。
【００３８】出力回路の共振周波数は負荷インピーダン
スとともに変化するので、前もって共振における変化を
単純に判断することは不可能である。というのは、い
つ、またはどの周波数で、それらの変化が生じるかとい
うことを前もって知るのは不可能だからである。したが
って、図４のシステムにおけるジェネレータは補償構成
を含み、ここに電圧計１７６からの出力を正常にするた
めの変調基準を含む。再び図４を参照して、この補償構
成はジェネレータ出力変圧器１８２の主な巻線にわたっ
て接続される検出回路１８０を有する。この変調検出回
路１８０は抵抗１９６およびキャパシタ１８８と直列に
ダイオード１８４を含む。電圧計１９０およびさらなる
抵抗１９１は、キャパシタ１８８と並列に接続され、電
圧計１９０はジェネレータ出力における変調の瞬時深さ
を検出し、これを用いて変調基準を与えることもでき、
それによって感知回路の電圧計１７６からの出力は電極
１３０における熱電子放出の効果のみを反映するよう
に、効果的に正常化され得る。
スとともに変化するので、前もって共振における変化を
単純に判断することは不可能である。というのは、い
つ、またはどの周波数で、それらの変化が生じるかとい
うことを前もって知るのは不可能だからである。したが
って、図４のシステムにおけるジェネレータは補償構成
を含み、ここに電圧計１７６からの出力を正常にするた
めの変調基準を含む。再び図４を参照して、この補償構
成はジェネレータ出力変圧器１８２の主な巻線にわたっ
て接続される検出回路１８０を有する。この変調検出回
路１８０は抵抗１９６およびキャパシタ１８８と直列に
ダイオード１８４を含む。電圧計１９０およびさらなる
抵抗１９１は、キャパシタ１８８と並列に接続され、電
圧計１９０はジェネレータ出力における変調の瞬時深さ
を検出し、これを用いて変調基準を与えることもでき、
それによって感知回路の電圧計１７６からの出力は電極
１３０における熱電子放出の効果のみを反映するよう
に、効果的に正常化され得る。
【００３９】本発明の使用は、水分を含む場（水中）の
電気外科手術に制限されるものではない。アーク放電
は、乾燥した場の手術におけるモノポーラまたはバイポ
ーラの電気外科手術用器具でも起こり、電力は上記と同
じ態様で熱電子効果を用いて制御することができる。ま
た、活動電極が断続的に組織と接触する状況における神
経の刺激を実質的に回避するために、直流オフセットし
きい値電圧を比較的低いレベルに設定することも可能で
ある。
電気外科手術に制限されるものではない。アーク放電
は、乾燥した場の手術におけるモノポーラまたはバイポ
ーラの電気外科手術用器具でも起こり、電力は上記と同
じ態様で熱電子効果を用いて制御することができる。ま
た、活動電極が断続的に組織と接触する状況における神
経の刺激を実質的に回避するために、直流オフセットし
きい値電圧を比較的低いレベルに設定することも可能で
ある。
【００４０】モノポーラの適用例においては、アーク放
電の強度はアーク部位とリターン電極との間の導電経路
のインピーダンスに依存しており、インピーダンスが低
いとピークアーク電流は増加し、したがって温度および
切断速度も増加し、さらに神経刺激に関しても向上す
る。その結果、熱電子効果の感知を用いる電極温度に従
って（電極温度における変化を減じるために）電力を制
御すると、より一貫した組織の処置が達成できるように
なる。これにより、切断の質は向上し、電圧制御のみに
頼った電気外科手術の動作と比較すると、たとえば切断
部位近傍の組織の損傷および焦げ目の形成が減じられ
る。
電の強度はアーク部位とリターン電極との間の導電経路
のインピーダンスに依存しており、インピーダンスが低
いとピークアーク電流は増加し、したがって温度および
切断速度も増加し、さらに神経刺激に関しても向上す
る。その結果、熱電子効果の感知を用いる電極温度に従
って（電極温度における変化を減じるために）電力を制
御すると、より一貫した組織の処置が達成できるように
なる。これにより、切断の質は向上し、電圧制御のみに
頼った電気外科手術の動作と比較すると、たとえば切断
部位近傍の組織の損傷および焦げ目の形成が減じられ
る。
【００４１】電気外科手術用ジェネレータにおける熱電
子フィードバックは、組織の切除および切断速度の向
上、近傍組織の損傷および焦げめ形成の減少の可能性、
および神経刺激の減少を含む、多くの利点を提供する。
子フィードバックは、組織の切除および切断速度の向
上、近傍組織の損傷および焦げめ形成の減少の可能性、
および神経刺激の減少を含む、多くの利点を提供する。
【００４２】電極にアーク放電が存在することにより生
じる熱電子効果をフィードバック機構の刺激としてこの
明細書に記載のように用いると、実質的な電極の損傷な
しに比較的高電力の密度で電気外科手術を行なうことが
可能になる。したがって、白金などの高融点材料を用い
ると、非常に高い組織切断および組織除去の電力密度が
達成され、または電力密度が与えられている場合は、比
較的安価な、低い融点の金属または合金（たとえばステ
ンレス鋼など）を安全に用いることもできる。ここに記
載のシステムはまた、電極の誤使用の可能性およびその
結果生じる電極の損傷を減じるために用いられ得る。大
きなアーク放電を維持する能力により、活動電極が組織
と接触する可能性は減少し、したがって神経刺激の可能
性も減少する。
じる熱電子効果をフィードバック機構の刺激としてこの
明細書に記載のように用いると、実質的な電極の損傷な
しに比較的高電力の密度で電気外科手術を行なうことが
可能になる。したがって、白金などの高融点材料を用い
ると、非常に高い組織切断および組織除去の電力密度が
達成され、または電力密度が与えられている場合は、比
較的安価な、低い融点の金属または合金（たとえばステ
ンレス鋼など）を安全に用いることもできる。ここに記
載のシステムはまた、電極の誤使用の可能性およびその
結果生じる電極の損傷を減じるために用いられ得る。大
きなアーク放電を維持する能力により、活動電極が組織
と接触する可能性は減少し、したがって神経刺激の可能
性も減少する。
【００４３】本発明の好ましい実施例は、電気外科手術
用ジェネレータユニット内（すなわちそのようなユニッ
トのケーシング内）の回路を用いて熱電子効果を感知す
るというシステムであるが、ジェネレータの出力端子と
電気外科手術用器具との間の導電経路内で結合されたア
ドオン(add-on)モジュールにおいて本発明を具体化する
ことも可能である。このモジュールは、ジェネレータユ
ニットのソケット１０Ｓ内に適合するそれ自身のコネク
タと、図１に示す接続コード１４上のプラグアセンブリ
を受けるためのソケットとを有し得る。オフセット電圧
を検出するための回路はモジュール内に含まれ、ジェネ
レータユニットと器具との間の導電経路を形成する線に
接続され、器具への電気外科手術用電力の伝達は、モジ
ュール内の可変インピーダンス素子によって、またはジ
ェネレータユニットの制御ユニットに制御信号を与える
ことによって、制御される。信頼性を高めるために、こ
こに記載のアドオンモジュールと別のジェネレータユニ
ットとの組合せが、請求の範囲に記載される本発明の範
囲内の電気外科手術用ジェネレータを構成するために考
慮される。
用ジェネレータユニット内（すなわちそのようなユニッ
トのケーシング内）の回路を用いて熱電子効果を感知す
るというシステムであるが、ジェネレータの出力端子と
電気外科手術用器具との間の導電経路内で結合されたア
ドオン(add-on)モジュールにおいて本発明を具体化する
ことも可能である。このモジュールは、ジェネレータユ
ニットのソケット１０Ｓ内に適合するそれ自身のコネク
タと、図１に示す接続コード１４上のプラグアセンブリ
を受けるためのソケットとを有し得る。オフセット電圧
を検出するための回路はモジュール内に含まれ、ジェネ
レータユニットと器具との間の導電経路を形成する線に
接続され、器具への電気外科手術用電力の伝達は、モジ
ュール内の可変インピーダンス素子によって、またはジ
ェネレータユニットの制御ユニットに制御信号を与える
ことによって、制御される。信頼性を高めるために、こ
こに記載のアドオンモジュールと別のジェネレータユニ
ットとの組合せが、請求の範囲に記載される本発明の範
囲内の電気外科手術用ジェネレータを構成するために考
慮される。
【００４４】ここに記載の実施例は、感知された熱電子
効果に応答してジェネレータ出力が制御および調節され
るという制御機能を果たすが、本発明はその範囲内に、
熱電子放出を感知するための手段が、たとえば外科医に
よって読み出されるための温度を提供するために、電極
温度の単なるインジケータとして用いられるシステムも
含む。
効果に応答してジェネレータ出力が制御および調節され
るという制御機能を果たすが、本発明はその範囲内に、
熱電子放出を感知するための手段が、たとえば外科医に
よって読み出されるための温度を提供するために、電極
温度の単なるインジケータとして用いられるシステムも
含む。
【図１】 本発明に従った電気外科手術システムを示す
図である。
図である。
【図２】 導電性の液体に浸漬されて用いられるところ
を示す、組織切除のための電極アセンブリの部分図であ
る。
を示す、組織切除のための電極アセンブリの部分図であ
る。
【図３】 ＡおよびＢは、直流オフセット検出器を含む
電気外科手術システムの回路図である。
電気外科手術システムの回路図である。
【図４】 本発明に従った代替的な電気外科手術システ
ムの回路図である。
ムの回路図である。
【図５】 図４のシステムの一部を形成するジェネレー
タの変調された出力電圧波形を示す波形図である。
タの変調された出力電圧波形を示す波形図である。
【図６】 図４に示すシステムの活動電極における熱電
子効果の存在下でのジェネレータ出力の波形、および出
力電圧の単一高周波サイクルにわたって平均される平均
出力電圧を示す、波形図である。
子効果の存在下でのジェネレータ出力の波形、および出
力電圧の単一高周波サイクルにわたって平均される平均
出力電圧を示す、波形図である。
６０ 高周波電源、６２，６３ キャパシタ、６４ 作
動電極、６６ リターン電極、７６ インピーダンスバ
ッファ、８２ オプトアイソレータ、８４ 比較器、８
６ ＯＲゲート、９０ 降圧変圧器、９２ ブリッジ整
流器。
動電極、６６ リターン電極、７６ インピーダンスバ
ッファ、８２ オプトアイソレータ、８４ 比較器、８
６ ＯＲゲート、９０ 降圧変圧器、９２ ブリッジ整
流器。
───────────────────────────────────────────────────── フロントページの続き (72)発明者 コリン・チャールズ・オーウェン・ゴーブ ル イギリス、シィ・エフ・64 １・エイ・テ ィ ウェールズ、サウス・グラモーガン、 ピナース、クリブ・クレセント、オズボー ン・ハウス、５
Claims (31)
- 【請求項１】 電気外科手術用器具の処置電極に供給す
るための高周波エネルギ源を含むジェネレータを含み、
前記ジェネレータは電極からの熱電子放出を感知するた
めの回路を含む、電気外科手術システム。 - 【請求項２】 感知回路からの出力信号に応答して処置
電極に供給された高周波エネルギを制御するように動作
可能な制御回路を含み、前記感知回路および制御回路
は、電極からの熱電子放出が増加すると与えられた高周
波エネルギが減少するように構成される、請求項１に記
載のシステム。 - 【請求項３】 感知回路が、ジェネレータの動作周波数
で実質上高周波信号を取除いてジェネレータの高周波出
力の平均化された表示を生じるように構成された入力ス
テージと、前記平均化された表示を受けるように入力ス
テージに結合された検出ステージとを有する、請求項１
または請求項２に記載のシステム。 - 【請求項４】 前記ジェネレータが、処置電極に接続す
るための出力端子を有し、感知回路が、２ボルトより高
い予め定められた電圧範囲内の出力端子直流電圧を検出
するように構成される、請求項１から請求項３のいずれ
かに記載のシステム。 - 【請求項５】 前記感知回路が、検出された直流電圧が
予め定められたしきい値を超えるとしきい値信号を発生
するように構成される、請求項４に記載のシステム。 - 【請求項６】 しきい値が１０Ｖから１００Ｖの範囲に
ある、請求項５に記載のシステム。 - 【請求項７】 前記ジェネレータが、電気外科手術用器
具の処置電極に供給するための変調高周波出力を発生す
るように構成され、前記感知回路が、ジェネレータ動作
周波数での高周波信号を実質的に取り除くことにより、
平均化された信号が平均化信号の振幅の測定値として感
知回路信号を生成する検出ステージに供給されるように
構成される、請求項３に記載のシステム。 - 【請求項８】 感知回路の入力ステージが、変調の周波
数を含みジェネレータの動作周波数は含まない通過域を
有するフィルタを含み、平均信号が変調周波数と同等の
周波数を有する交流信号である、請求項７に記載のシス
テム。 - 【請求項９】 前記ジェネレータが、それぞれのジェネ
レータ出力端子に結合された１対の出力線を有する出力
ステージを有し、各出力線は直列接続された分離キャパ
シタと、それぞれの分離キャパシタと出力端子との間の
出力線の１つに直列インダクタンスとを有し、このイン
ダクタンスが感知回路の入力ステージに結合されてい
る、請求項８に記載のシステム。 - 【請求項１０】 前記入力ステージが、変調周波数に同
調され、かつ前記直列インダクタンスに帰納的に結合さ
れたインダクタンスを有する平衡共振回路を含み、前記
検出回路が、共振回路にわたって結合されて共振回路に
わたって発達した信号の振幅を検出する、請求項９に記
載のシステム。 - 【請求項１１】 高周波エネルギ源を含むジェネレータ
と、ジェネレータに結合されて、処置電極を有する電気
外科手術用器具とを含む、電気外科手術システムであっ
て、前記システムは、処置電極において２ボルトを超え
る直流オフセットを検出するように構成される直流電圧
検出器と、この検出器に結合されて、直流オフセットに
応答して前記器具に与えられる高周波エネルギを制御す
るための制御回路とを含む、電気外科手術システム。 - 【請求項１２】 前記制御回路および検出器は、直流オ
フセットを予め定められた直流電圧レベルに制限するよ
うに動作可能である、請求項１１に記載のシステム。 - 【請求項１３】 前記制御回路および検出器は、直流オ
フセットを５０Ｖから１００Ｖの範囲の予め設定された
値に制限するように動作可能である、請求項１１に記載
のシステム。 - 【請求項１４】 前記ジェネレータは、処置電極に接続
可能な出力端子を有し、前記検出器は、出力端子に結合
された検出入力と、検出器を制御回路に接続するアイソ
レーション装置とを有する、請求項１１から請求項１３
のいずれかに記載のシステム。 - 【請求項１５】 前記検出器は、ジェネレータの高周波
出力エネルギから電力を与えられ、この検出器は、前記
出力端子に結合された電源回路と、出力端子に与えられ
る高周波電気外科手術信号を整流するための整流器とを
含む、請求項１４に記載のシステム。 - 【請求項１６】 前記検出器が、直流オフセットを表わ
す交互に変わる測定信号を発生するための発振器を含
み、前記アイソレーション装置が、交互に変わる測定信
号を受けるために、また制御回路にそれを供給するため
に結合されたオプトアイソレータを含む、請求項１４ま
たは請求項１５に記載のシステム。 - 【請求項１７】 前記検出器が、（ａ）予め定められた
電圧値より大きい正の直流オフセットおよび（ｂ）負の
直流オフセットの両方の検出を可能にする反転直流オフ
セット検出回路を含む、請求項１１から請求項１６のい
ずれかに記載のシステム。 - 【請求項１８】 前記検出器が、ジェネレータの出力端
子に結合された入力回路を有し、その入力回路が高周波
チョークおよび少なくとも２ＭΩの直列抵抗を含む、請
求項１４から請求項１６のいずれかに記載のシステム。 - 【請求項１９】 高周波エネルギ源と、 活動出力端子と、 リターン出力端子と、 エネルギ源と活動出力端子との間の直流分離キャパシタ
と、 ２ボルトを超える直流オフセット電圧を検出するために
分離キャパシタの出力端子側に接続された分路入力を有
する直流オフセット検出器と、 前記分路入力における直流オフセット電圧に応答して活
動出力端子に与えられた高周波エネルギを制御するため
にエネルギ源に結合された制御回路とを含む、 電気外科手術用ジェネレータ。 - 【請求項２０】 前記制御回路および検出器は、直流オ
フセットを予め定められた直流電圧レベルに制限するよ
うに動作可能である、請求項１９に記載のジェネレー
タ。 - 【請求項２１】 直流オフセットを５０Ｖから１００Ｖ
の領域の予め設定された値に制限するように動作可能で
ある、請求項２０に記載のジェネレータ。 - 【請求項２２】 前記検出器が、前記検出器を制御回路
に接続するアイソレーション装置を有する、請求項１９
から請求項２１のいずれかに記載のジェネレータ。 - 【請求項２３】 前記検出器が、前記活動端子とリター
ン端子との間に接続された電源回路と、出力端子にわた
って与えられる高周波電気外科手術用信号を整流するた
めの整流器とを含む、請求項２２に記載のジェネレー
タ。 - 【請求項２４】 前記検出器が、直流オフセットを表わ
す交互に変わる測定信号を発生するための発振器を含
み、前記アイソレーション装置が、交互に変わる測定信
号を受けてそれを制御回路に供給するように結合される
オプトアイソレータを含む、請求項２２または請求項２
３に記載のジェネレータ。 - 【請求項２５】 前記検出器が、（ａ）予め定められた
電圧値より大きい正の直流オフセットおよび（ｂ）活動
出力端子における負の直流オフセットの両方の検出を可
能にする反転直流オフセット検出回路を含む、請求項１
９から請求項２４のいずれかに記載のジェネレータ。 - 【請求項２６】 前記検出器が、ジェネレータ出力端子
に結合された入力回路を有し、この入力回路が、高周波
チョークおよび少なくとも２ＭΩの直列抵抗を含む、請
求項２２から請求項２４のいずれかに記載のジェネレー
タ。 - 【請求項２７】 電気外科手術で組織の切断または切除
を行なうための方法であって、電気外科手術用器具に高
周波エネルギが与えられることによりこの器具の処置電
極におけるアーク放電を促進し、そのようなエネルギの
レベルが電極からの熱電子放出のレベルに従って調節さ
れている、方法。 - 【請求項２８】 高周波エネルギが、実質的な電極の燃
焼を伴わずに電極の温度を最大にするように調節され
る、請求項２７に記載の方法。 - 【請求項２９】 高周波エネルギが、直流電圧を１００
Ｖ未満のしきい値に制限するように調節される、請求項
２７に記載の方法。 - 【請求項３０】 ジェネレータ動作周波数で動作可能な
高周波電源と、１対の高周波電力出力端子を含む出力ス
テージとを含む電気外科手術用ジェネレータであって、
前記出力ステージは電源からＤＣ分離されている出力ス
テージであり、前記ジェネレータはさらに、電源によっ
て発生された高周波電力信号を変調するための手段と、
出力ステージにＡＣ結合され出力ステージからＤＣ分離
されて、出力端子に伝達される電力信号におけるＤＣシ
フトを表わす変調成分を含む平均化されたＡＣ信号を発
生するように動作可能である感知回路とを含む、電気外
科手術用ジェネレータ。 - 【請求項３１】 前記変調手段は、予め定められた変調
周波数で高周波電力信号における振幅変調を生成し、前
記ジェネレータはさらに、入力から感知回路への動作周
波数で高周波成分を実質的に取除いて平均化されたＡＣ
信号をもたらすための感知回路に関連づけられるフィル
タリング要素を含む、請求項３０に記載のジェネレー
タ。
Applications Claiming Priority (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| GB9911954:7 | 1999-05-21 | ||
| GBGB9911954.7A GB9911954D0 (en) | 1999-05-21 | 1999-05-21 | Electrosurgery system and instrument |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| JP2000350732A true JP2000350732A (ja) | 2000-12-19 |
Family
ID=10853980
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP2000147958A Withdrawn JP2000350732A (ja) | 1999-05-21 | 2000-05-19 | 電気外科手術システム、電気外科手術用ジェネレータ、および電気外科手術で組織を切断または切除するための方法 |
Country Status (7)
| Country | Link |
|---|---|
| EP (1) | EP1053719A1 (ja) |
| JP (1) | JP2000350732A (ja) |
| CN (1) | CN1274566A (ja) |
| AU (1) | AU3540600A (ja) |
| BR (1) | BR0013450A (ja) |
| CA (1) | CA2308879A1 (ja) |
| GB (1) | GB9911954D0 (ja) |
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Also Published As
| Publication number | Publication date |
|---|---|
| CN1274566A (zh) | 2000-11-29 |
| GB9911954D0 (en) | 1999-07-21 |
| AU3540600A (en) | 2000-11-23 |
| CA2308879A1 (en) | 2000-11-21 |
| EP1053719A1 (en) | 2000-11-22 |
| BR0013450A (pt) | 2002-04-23 |
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