JP2001029356A - 電気外科用信号発生器 - Google Patents
電気外科用信号発生器Info
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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
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Abstract
(57)【要約】
【課題】 治療中の組織の変化等に起因するインピーダ
ンスの変化を検出して自動的に出力電力を変更する電気
外科用信号発生器を提供する。 【解決手段】 電気外科用信号発生器は、発生器の無線
周波数出力から反射して戻される電力の変化を検出する
ための検出回路と、反射電力モニタ用信号を処理するた
めに検出回路に接続される制御装置とを備える。制御装
置は、治療中の組織の状態の変化に起因する反射電力の
変化を示すモニタ用信号の所定の状態に応じて、発生器
出力への無線周波数電力の適用を減少或いは停止するよ
うに動作する。発生器は、300MHz以上及び未満で
それぞれ動作可能な上側周波数部及び下側周波数部を有
し、両周波数部が発生器出力に接続され、また制御装置
は、下側周波数部の動作周波数で検出される負荷インピ
ーダンスが変化する際に、適用された無線周波数電力を
減少或いは遮断する。
ンスの変化を検出して自動的に出力電力を変更する電気
外科用信号発生器を提供する。 【解決手段】 電気外科用信号発生器は、発生器の無線
周波数出力から反射して戻される電力の変化を検出する
ための検出回路と、反射電力モニタ用信号を処理するた
めに検出回路に接続される制御装置とを備える。制御装
置は、治療中の組織の状態の変化に起因する反射電力の
変化を示すモニタ用信号の所定の状態に応じて、発生器
出力への無線周波数電力の適用を減少或いは停止するよ
うに動作する。発生器は、300MHz以上及び未満で
それぞれ動作可能な上側周波数部及び下側周波数部を有
し、両周波数部が発生器出力に接続され、また制御装置
は、下側周波数部の動作周波数で検出される負荷インピ
ーダンスが変化する際に、適用された無線周波数電力を
減少或いは遮断する。
Description
【0001】
【発明の属する技術分野】本発明は、出力電力が自動的
に調整可能な電気外科用信号発生器に関する。
に調整可能な電気外科用信号発生器に関する。
【0002】電気外科治療の分野では、特に必要な組織
の変化が生じている状況にある治療中の組織への電力の
送給を自動的に調整できることが望まれる。生体組織或
いはその周辺に位置する物質が電気外科レベルの無線周
波数(RF)エネルギーを加えられることにより影響を
受ける場合、その電気的特性、特に導電率及び誘電率に
変化が生じる。従って、その組織或いは他の物質により
電気外科治療器具に与えられる電気的負荷インピーダン
スは、組織或いは他の物質の状態の関数として変化す
る。
の変化が生じている状況にある治療中の組織への電力の
送給を自動的に調整できることが望まれる。生体組織或
いはその周辺に位置する物質が電気外科レベルの無線周
波数(RF)エネルギーを加えられることにより影響を
受ける場合、その電気的特性、特に導電率及び誘電率に
変化が生じる。従って、その組織或いは他の物質により
電気外科治療器具に与えられる電気的負荷インピーダン
スは、組織或いは他の物質の状態の関数として変化す
る。
【0003】本発明の一態様に従えば、電気外科用信号
発生器は、電気外科用電極アセンブリに接続される発生
器出力に接続される無線周波数電力源と、出力からフィ
ードバックされた反射電力の変化を検出するよう動作可
能な検出回路と、検出回路からのモニタ用信号を処理す
るために検出回路に接続される入力、及び電力源の出力
電力を調整するために電力源に接続される電力制御出力
を備える制御装置とを備え、制御装置が、治療中の組織
の状態の変化に起因する反射電力の変化を示すモニタ用
信号の所定の条件に応じて、電力源から発生器出力に加
えられる無線周波数電力を低減或いは停止するように構
成される。
発生器は、電気外科用電極アセンブリに接続される発生
器出力に接続される無線周波数電力源と、出力からフィ
ードバックされた反射電力の変化を検出するよう動作可
能な検出回路と、検出回路からのモニタ用信号を処理す
るために検出回路に接続される入力、及び電力源の出力
電力を調整するために電力源に接続される電力制御出力
を備える制御装置とを備え、制御装置が、治療中の組織
の状態の変化に起因する反射電力の変化を示すモニタ用
信号の所定の条件に応じて、電力源から発生器出力に加
えられる無線周波数電力を低減或いは停止するように構
成される。
【0004】好適な発生器では、無線周波数(RF)電
力源は、300MHz以上で動作するように構成され、
3ポートのインピーダンスアイソレータが、無線周波数
電力源と発生器出力との間の順方向電力経路、及び発生
器出力と抵抗性のダンプ用負荷との間の反射電力経路に
接続される。検出回路は、無線周波数電力源と発生器出
力との間、或いはアイソレータとダンプ用の負荷との間
の出力ラインの反射電力経路部分に関連する方向性結合
器を備えることもできる。その好適な形態では、検出回
路は、発生器出力から反射して戻される電力を表す電圧
或いは電流信号を供給するように構成され、この信号
は、検出器及びともにモニタ用信号を与える信号調整段
に給送される。インピーダンスアイソレータはサーキュ
レータ或いはハイブリッド結合器を含むこともできる。
力源は、300MHz以上で動作するように構成され、
3ポートのインピーダンスアイソレータが、無線周波数
電力源と発生器出力との間の順方向電力経路、及び発生
器出力と抵抗性のダンプ用負荷との間の反射電力経路に
接続される。検出回路は、無線周波数電力源と発生器出
力との間、或いはアイソレータとダンプ用の負荷との間
の出力ラインの反射電力経路部分に関連する方向性結合
器を備えることもできる。その好適な形態では、検出回
路は、発生器出力から反射して戻される電力を表す電圧
或いは電流信号を供給するように構成され、この信号
は、検出器及びともにモニタ用信号を与える信号調整段
に給送される。インピーダンスアイソレータはサーキュ
レータ或いはハイブリッド結合器を含むこともできる。
【0005】そのような発生器を用いる場合、必要とさ
れる組織の状態が十分なエネルギー伝達を通して一旦達
成され、それ以上組織を変更する必要がない場合(例え
ば2つの組織構造が互いに接合される)場合には、組織
の変更を終了することができる。例えば、出血を止める
ための凝固の効率的な手段として無線周波数電力を送給
する場合等におけるように、不要な組織の影響は避けら
れるか、或いは最小にされる。この場合、電極が除去さ
れる際に組織が引き裂かれないようにするために、凝固
剤が電極アセンブリの電極に付着する前に、エネルギー
を加えるのを止めることが望ましい。また発生器は、低
周波エネルギーを用いて組織を切断並びに/または気化
(蒸発)させる前に、UHFエネルギーを用いて組織を
事前に凝固する場合のように、2段階の処置が必要とさ
れる場合には有用である。この場合、検出回路及び制御
装置はともに、無線周波数電力源出力を、エネルギーが
主に第1の周波数範囲において供給される出力から、エ
ネルギーが主に第2の異なる周波数範囲において供給さ
れる出力に変更するために、予備の治療が終了したこと
を検出するように動作させることもできる。
れる組織の状態が十分なエネルギー伝達を通して一旦達
成され、それ以上組織を変更する必要がない場合(例え
ば2つの組織構造が互いに接合される)場合には、組織
の変更を終了することができる。例えば、出血を止める
ための凝固の効率的な手段として無線周波数電力を送給
する場合等におけるように、不要な組織の影響は避けら
れるか、或いは最小にされる。この場合、電極が除去さ
れる際に組織が引き裂かれないようにするために、凝固
剤が電極アセンブリの電極に付着する前に、エネルギー
を加えるのを止めることが望ましい。また発生器は、低
周波エネルギーを用いて組織を切断並びに/または気化
(蒸発)させる前に、UHFエネルギーを用いて組織を
事前に凝固する場合のように、2段階の処置が必要とさ
れる場合には有用である。この場合、検出回路及び制御
装置はともに、無線周波数電力源出力を、エネルギーが
主に第1の周波数範囲において供給される出力から、エ
ネルギーが主に第2の異なる周波数範囲において供給さ
れる出力に変更するために、予備の治療が終了したこと
を検出するように動作させることもできる。
【0006】電気外科的な治療中に、組織及び関連する
物質の状態が繰返し変化することを観測することができ
る。例えば治療中の組織内の液体及び治療中の組織の領
域にある液体は、治療中に沸騰するか、或いは電極付近
の物質が振動するように動かされ、そのいずれの効果
も、負荷インピーダンスが繰返し変化することに起因し
て反射電力信号を変調するようになる。そのような変調
は、検出回路の一部を形成する復調器により検出するこ
とができ、制御装置及び信号調整段が、検出信号により
表される変調が所定の閾値レベルを超える場合、すなわ
ちその検出信号が、それが現れた後に、変調が減少して
いるか、その後に停止したことを示す場合、電力源の出
力電力を低下させるように構成される。
物質の状態が繰返し変化することを観測することができ
る。例えば治療中の組織内の液体及び治療中の組織の領
域にある液体は、治療中に沸騰するか、或いは電極付近
の物質が振動するように動かされ、そのいずれの効果
も、負荷インピーダンスが繰返し変化することに起因し
て反射電力信号を変調するようになる。そのような変調
は、検出回路の一部を形成する復調器により検出するこ
とができ、制御装置及び信号調整段が、検出信号により
表される変調が所定の閾値レベルを超える場合、すなわ
ちその検出信号が、それが現れた後に、変調が減少して
いるか、その後に停止したことを示す場合、電力源の出
力電力を低下させるように構成される。
【0007】別法では、反射電力の変化率或いは反射電
力の変調は、モニタされるべき組織の状態により検出す
ることもできる。反射電力信号は、デュアルチャネル検
出器及び信号調整装置に加えられるようになるが、チャ
ネルの1つが、例えば平均処理手段を備えており、各チ
ャネルの出力に接続された入力を有するコンパレータ
が、反射電力に関連する特性の短時間の変化を表すセン
サ出力信号を生成できるようにする。これにより、治療
電極の動きに起因するインピーダンス及び反射電力の変
化のような比較的低速の影響が相殺されるようにする。
力の変調は、モニタされるべき組織の状態により検出す
ることもできる。反射電力信号は、デュアルチャネル検
出器及び信号調整装置に加えられるようになるが、チャ
ネルの1つが、例えば平均処理手段を備えており、各チ
ャネルの出力に接続された入力を有するコンパレータ
が、反射電力に関連する特性の短時間の変化を表すセン
サ出力信号を生成できるようにする。これにより、治療
電極の動きに起因するインピーダンス及び反射電力の変
化のような比較的低速の影響が相殺されるようにする。
【0008】一般的な観点では、本発明は、組織のイン
ピーダンス及び給送構造の差の結果として生じる高周波
反射電力の変化を利用する。発生器の一部を形成し、反
射電力を測定するために発生器出力に接続される検出器
が、組織の状態に関する判定が自動的に行われるように
する、振幅並びに/または位相情報を含む電圧或いは電
流信号を生成することができる。組織の電気的特性が変
化する場合、反射信号の振幅及び位相が変化する。ある
組織の影響により、振幅、位相或いは周波数変調を生じ
る電極に与えられる負荷インピーダンスに急激な変動が
生じるようになる。変調の存在及びそのような変調の特
性は、最適な電力給送を達成し、組織の変化率を制御す
るために、組織の状態が変化する場合、本発明による電
力給送を制御するために用いることができる組織の変化
或いは他のプロセスを示すことができる。
ピーダンス及び給送構造の差の結果として生じる高周波
反射電力の変化を利用する。発生器の一部を形成し、反
射電力を測定するために発生器出力に接続される検出器
が、組織の状態に関する判定が自動的に行われるように
する、振幅並びに/または位相情報を含む電圧或いは電
流信号を生成することができる。組織の電気的特性が変
化する場合、反射信号の振幅及び位相が変化する。ある
組織の影響により、振幅、位相或いは周波数変調を生じ
る電極に与えられる負荷インピーダンスに急激な変動が
生じるようになる。変調の存在及びそのような変調の特
性は、最適な電力給送を達成し、組織の変化率を制御す
るために、組織の状態が変化する場合、本発明による電
力給送を制御するために用いることができる組織の変化
或いは他のプロセスを示すことができる。
【0009】本発明の第2の態様に従えば、電気外科用
信号発生器は、300MHz以上で動作可能な上側周波
数部及び300MHz未満で動作可能な下側周波数部を
備える無線周波数(RF)電力源と、電力源の両方の部
分(上側および下側周波数部)が接続されており、電気
外科電極アセンブリに接続するための発生器出力と、電
力源の下側周波数部の動作周波数(単数または複数)に
おいて負荷インピーダンスを検出するための負荷インピ
ーダンスセンサを備える検出回路と、検出回路からのモ
ニタ用信号を処理するために検出回路に接続される入力
及び電力源の電力出力を調整するために電力源に接続さ
れる電力制御出力を備える制御装置とを備え、制御装置
は、電力源の下側周波数部の動作周波数(単数または複
数)において検出される負荷インピーダンスの変化を示
すモニタ用信号の所定の条件に応じて、電力源の上側周
波数部から発生器出力までの無線周波数電力の供給を低
減或いは停止するように構成される。負荷インピーダン
スセンサは、電力源の下側周波数部と発生器出力との間
の出力ラインに接続される電圧及び電流測定回路を備え
ることができる。或いは、電力源の下側周波数部の動作
周波数が負荷インピーダンスに依存する場合に、負荷イ
ンピーダンスセンサは下側周波数部の周波数を検出す
る。
信号発生器は、300MHz以上で動作可能な上側周波
数部及び300MHz未満で動作可能な下側周波数部を
備える無線周波数(RF)電力源と、電力源の両方の部
分(上側および下側周波数部)が接続されており、電気
外科電極アセンブリに接続するための発生器出力と、電
力源の下側周波数部の動作周波数(単数または複数)に
おいて負荷インピーダンスを検出するための負荷インピ
ーダンスセンサを備える検出回路と、検出回路からのモ
ニタ用信号を処理するために検出回路に接続される入力
及び電力源の電力出力を調整するために電力源に接続さ
れる電力制御出力を備える制御装置とを備え、制御装置
は、電力源の下側周波数部の動作周波数(単数または複
数)において検出される負荷インピーダンスの変化を示
すモニタ用信号の所定の条件に応じて、電力源の上側周
波数部から発生器出力までの無線周波数電力の供給を低
減或いは停止するように構成される。負荷インピーダン
スセンサは、電力源の下側周波数部と発生器出力との間
の出力ラインに接続される電圧及び電流測定回路を備え
ることができる。或いは、電力源の下側周波数部の動作
周波数が負荷インピーダンスに依存する場合に、負荷イ
ンピーダンスセンサは下側周波数部の周波数を検出す
る。
【0010】当然ではあるが、治療中の組織の状態或い
は外科治療の実施形態により(例えば、凝固或いは組織
の切断並びに/または気化(蒸発))、300MHz以
上の反射周波数をモニタするばかりでなく、300MH
z未満の周波数において発生器出力に与えられる負荷イ
ンピーダンスもモニタすることにより、300MHz以
上の周波数における電力の給送を制御することもでき
る。負荷インピーダンスが検出されている時、下側周波
数部の動作周波数(単数または複数)において発生器出
力に与えられる検出された負荷インピーダンスが所定の
閾値より大きくなる場合には、電力源の上側周波数部か
ら電力を加えることは、制御装置により低減或いは停止
されるようになる。必ずしも下側周波数部が、電気外科
的な効果をもたらすだけの十分なレベルで電力を給送す
るとは限らない。実際には、検出回路が、負荷インピー
ダンスを示すモニタ用信号を生成することができるのに
十分なだけのレベルの信号を生成することができる。
は外科治療の実施形態により(例えば、凝固或いは組織
の切断並びに/または気化(蒸発))、300MHz以
上の反射周波数をモニタするばかりでなく、300MH
z未満の周波数において発生器出力に与えられる負荷イ
ンピーダンスもモニタすることにより、300MHz以
上の周波数における電力の給送を制御することもでき
る。負荷インピーダンスが検出されている時、下側周波
数部の動作周波数(単数または複数)において発生器出
力に与えられる検出された負荷インピーダンスが所定の
閾値より大きくなる場合には、電力源の上側周波数部か
ら電力を加えることは、制御装置により低減或いは停止
されるようになる。必ずしも下側周波数部が、電気外科
的な効果をもたらすだけの十分なレベルで電力を給送す
るとは限らない。実際には、検出回路が、負荷インピー
ダンスを示すモニタ用信号を生成することができるのに
十分なだけのレベルの信号を生成することができる。
【0011】
【発明の実施の形態】次に、本発明について図面を参照
しつつ例を用いて説明する。
しつつ例を用いて説明する。
【0012】図1を参照すると、本発明による発生器1
0は、周波数発生源12と電力増幅器14とを備える無
線周波数源を有する。周波数発生源12は1つ或いは複
数の周波数シンセサイザの形をとることができ、その周
波数は制御システム16により制御される。
0は、周波数発生源12と電力増幅器14とを備える無
線周波数源を有する。周波数発生源12は1つ或いは複
数の周波数シンセサイザの形をとることができ、その周
波数は制御システム16により制御される。
【0013】好適な発生器は、電力増幅器出力14Aと
発生器出力端子21との間にある出力ライン20のよう
な順方向電力経路を接続するサーキュレータのようなイ
ンピーダンスアイソレータ18を介してUHF帯で電気
外科用電力を供給する。逆方向の電力経路では、インピ
ーダンスアイソレータは、逆方向電力出力23Aにおい
て逆方向に向かう電力部分信号を生成するための方向性
結合器23を介してダンプ用負荷22に発生器出力端子
21を接続する。図1では、出力端子21は、治療電極
を有する電極アセンブリ24に接続されることが示され
ており、治療電極は使用中に患者26、詳細には治療さ
れるべき組織に適用される。
発生器出力端子21との間にある出力ライン20のよう
な順方向電力経路を接続するサーキュレータのようなイ
ンピーダンスアイソレータ18を介してUHF帯で電気
外科用電力を供給する。逆方向の電力経路では、インピ
ーダンスアイソレータは、逆方向電力出力23Aにおい
て逆方向に向かう電力部分信号を生成するための方向性
結合器23を介してダンプ用負荷22に発生器出力端子
21を接続する。図1では、出力端子21は、治療電極
を有する電極アセンブリ24に接続されることが示され
ており、治療電極は使用中に患者26、詳細には治療さ
れるべき組織に適用される。
【0014】インピーダンスアイソレータ18及びダン
プ用負荷22により、公称50Ωインピーダンスが電力
増幅器出力14Aに与えられるようになる。電力増幅器
出力14Aが十分に定格される場合には、それらの構成
要素は省略することができる。
プ用負荷22により、公称50Ωインピーダンスが電力
増幅器出力14Aに与えられるようになる。電力増幅器
出力14Aが十分に定格される場合には、それらの構成
要素は省略することができる。
【0015】方向性結合器23は無線周波数源12、1
4と電極アセンブリ24との間に直列に接続され、検出
回路28の一部を形成する。結合器の逆方向電力出力2
3Aは、反射された電力を表す逆方向電力部分信号を供
給し、逆方向電力部分信号を処理するために検出及び信
号調整段29に接続される。
4と電極アセンブリ24との間に直列に接続され、検出
回路28の一部を形成する。結合器の逆方向電力出力2
3Aは、反射された電力を表す逆方向電力部分信号を供
給し、逆方向電力部分信号を処理するために検出及び信
号調整段29に接続される。
【0016】発生器10と、電極アセンブリ24及びそ
の周辺物(患者26を含む)により与えられる電気的負
荷との間に完全な共役インピーダンスの一致がなけれ
ば、発生器の出力端子26から電極アセンブリまで給送
される電力のうちのある量が反射電力として戻される。
これは、反射電力の大きさを示す反射電力出力信号を供
給する電圧として、検出及び信号調整段29の受信機或
いは検出器により測定される。
の周辺物(患者26を含む)により与えられる電気的負
荷との間に完全な共役インピーダンスの一致がなけれ
ば、発生器の出力端子26から電極アセンブリまで給送
される電力のうちのある量が反射電力として戻される。
これは、反射電力の大きさを示す反射電力出力信号を供
給する電圧として、検出及び信号調整段29の受信機或
いは検出器により測定される。
【0017】さらに信号調整段29が行うこの信号の処
理は、例えば、制御システム16のモニタ用入力16A
に給送されるモニタ用信号を発生させる、反射電力の変
調を処理することである。制御システム16は、センサ
出力信号を用いて、組織に変化が生じる時点を判定し、
その結果、電力増幅器14に接続された制御出力16B
により発生器の電力出力を低減或いは終息させる。
理は、例えば、制御システム16のモニタ用入力16A
に給送されるモニタ用信号を発生させる、反射電力の変
調を処理することである。制御システム16は、センサ
出力信号を用いて、組織に変化が生じる時点を判定し、
その結果、電力増幅器14に接続された制御出力16B
により発生器の電力出力を低減或いは終息させる。
【0018】図2を参照すると、反射電力を測定するた
めの別の装置は、インピーダンスアイソレータ18とダ
ンプ用負荷22との間にある逆方向電力経路内に位置す
る方向性結合器23´を有する。この方向付けの利点
は、方向性結合器の電力定格要件が低電力であるのに対
して、上記実施形態は、双方向結合器を用いて、他の制
御のために逆方向電力測定と順方向電力測定とを一体化
できるようにすることである。
めの別の装置は、インピーダンスアイソレータ18とダ
ンプ用負荷22との間にある逆方向電力経路内に位置す
る方向性結合器23´を有する。この方向付けの利点
は、方向性結合器の電力定格要件が低電力であるのに対
して、上記実施形態は、双方向結合器を用いて、他の制
御のために逆方向電力測定と順方向電力測定とを一体化
できるようにすることである。
【0019】図3を参照すると、第3の実施例では、逆
方向電力フィードバック部分信号が、発生器出力端子2
1からの逆方向電力用のダンプ抵抗としても機能する抵
抗性の高電力減衰器30の出力から取り出される。
方向電力フィードバック部分信号が、発生器出力端子2
1からの逆方向電力用のダンプ抵抗としても機能する抵
抗性の高電力減衰器30の出力から取り出される。
【0020】ここで検出及び信号調整段29の3つの代
替的な構成例は、発生器の出力21に存在する反射電力
の変調を検出するための検出器40を開示する図4A、
図4B及び図4Cを参照して記載される。
替的な構成例は、発生器の出力21に存在する反射電力
の変調を検出するための検出器40を開示する図4A、
図4B及び図4Cを参照して記載される。
【0021】検出器40は出力40Aを有する振幅変調
(AM)検出器である。出力40は、検出された振幅変
調を搬送する。図4Aを参照すると、制御システムは、
一方の入力が検出器40のAM出力40Aに直結され、
他方の入力が検出器40のAM出力40Aから給送され
る信号の時間平均値を受信するために接続されるコンパ
レータ44を備える。平均化処理は時間平均化モジュー
ル46により実行される。平均化モジュール46の時定
数T1は、コンパレータの第2の入力に給送される信号
が、例えば治療中の組織に対する電極アセンブリの向き
の変化に起因する反射電力信号の振幅の比較的遅い変化
により変動する基準レベルを構成するように配設され
る。このようにして、コンパレータ44から得られる出
力信号は概ね、反射電力信号の急激な変化、或いは組織
或いはその付近にある液体の沸騰のような組織の状態の
急激な変化に起因する変調の深さを表すように形成され
る。
(AM)検出器である。出力40は、検出された振幅変
調を搬送する。図4Aを参照すると、制御システムは、
一方の入力が検出器40のAM出力40Aに直結され、
他方の入力が検出器40のAM出力40Aから給送され
る信号の時間平均値を受信するために接続されるコンパ
レータ44を備える。平均化処理は時間平均化モジュー
ル46により実行される。平均化モジュール46の時定
数T1は、コンパレータの第2の入力に給送される信号
が、例えば治療中の組織に対する電極アセンブリの向き
の変化に起因する反射電力信号の振幅の比較的遅い変化
により変動する基準レベルを構成するように配設され
る。このようにして、コンパレータ44から得られる出
力信号は概ね、反射電力信号の急激な変化、或いは組織
或いはその付近にある液体の沸騰のような組織の状態の
急激な変化に起因する変調の深さを表すように形成され
る。
【0022】コンパレータ出力信号は、制御システム1
6と電力増幅器14との間にある電力制御接続部16B
を介して無線周波数源(図1、図2及び図3参照)の電
力増幅器14の出力電力レベルを制御するための制御シ
ステムの電力コントローラ部分に加えられる。電力コン
トローラは、治療電極付近で沸騰する液体を表すAM信
号に応じて、或いは沸騰状態が検出され、その後収まっ
た場合に、電力増幅器14により給送される電力を調整
するように構成可能である。達成されるべき組織の影響
により、制御システム16の電力コントローラは、振幅
変調が検出される場合(例えば変調の深さが所定の閾値
より大きくなる場合)、増幅器14の出力電力レベルを
低下するように構成することができ、その低下は、コン
パレータ出力信号が状態を変え、沸騰の減少を示すま
で、徐々に生じる。その後、コンパレータ出力レベルが
再び状態を変えるか、或いは電力増幅器14の初期設定
の出力電力レベルに達するまで、比較的小さなステップ
で電力を増加させることができる。
6と電力増幅器14との間にある電力制御接続部16B
を介して無線周波数源(図1、図2及び図3参照)の電
力増幅器14の出力電力レベルを制御するための制御シ
ステムの電力コントローラ部分に加えられる。電力コン
トローラは、治療電極付近で沸騰する液体を表すAM信
号に応じて、或いは沸騰状態が検出され、その後収まっ
た場合に、電力増幅器14により給送される電力を調整
するように構成可能である。達成されるべき組織の影響
により、制御システム16の電力コントローラは、振幅
変調が検出される場合(例えば変調の深さが所定の閾値
より大きくなる場合)、増幅器14の出力電力レベルを
低下するように構成することができ、その低下は、コン
パレータ出力信号が状態を変え、沸騰の減少を示すま
で、徐々に生じる。その後、コンパレータ出力レベルが
再び状態を変えるか、或いは電力増幅器14の初期設定
の出力電力レベルに達するまで、比較的小さなステップ
で電力を増加させることができる。
【0023】別法では、電力増幅器14からの電力出力
は、沸騰により誘発されるAMの停止が生じる場合に低
下させることができる。
は、沸騰により誘発されるAMの停止が生じる場合に低
下させることができる。
【0024】これらの技術を用いて、電極アセンブリ2
4の治療電極への組織の付着並びに/または凝固を防ぐ
こともできる。
4の治療電極への組織の付着並びに/または凝固を防ぐ
こともできる。
【0025】検出及び信号調整段の第2の形態では、図
4Bに示されるように、検出器40の第1の出力40A
からの振幅変調は、コンパレータ44の第1の入力に給
送するための勾配信号を得るために区別することがで
き、その区別は微分器モジュール50により実行され
る。これは、電極での活発な沸騰を示す、振幅変調のス
パイクにより表される、反射電力レベルの極端に速い変
化に応答するコンパレータ出力信号を生成する。
4Bに示されるように、検出器40の第1の出力40A
からの振幅変調は、コンパレータ44の第1の入力に給
送するための勾配信号を得るために区別することがで
き、その区別は微分器モジュール50により実行され
る。これは、電極での活発な沸騰を示す、振幅変調のス
パイクにより表される、反射電力レベルの極端に速い変
化に応答するコンパレータ出力信号を生成する。
【0026】図4Cに示されるさらに別の実施形態で
は、組織変化を示す振幅変調と、組織に関連する電極の
向き及び近さに起因する長時間の変化とを同様に区別す
ることが、それぞれ短い時定数T1及び長い時定数T2を
有し、その出力がコンパレータ44の第1及び第2の入
力にそれぞれ接続される第1及び第2の平均化回路5
4、56に、ぞれぞれ検出器40の出力40Aを接続す
ることにより行なわれる。時定数T2は時定数T1より1
0倍大きい範囲にある。
は、組織変化を示す振幅変調と、組織に関連する電極の
向き及び近さに起因する長時間の変化とを同様に区別す
ることが、それぞれ短い時定数T1及び長い時定数T2を
有し、その出力がコンパレータ44の第1及び第2の入
力にそれぞれ接続される第1及び第2の平均化回路5
4、56に、ぞれぞれ検出器40の出力40Aを接続す
ることにより行なわれる。時定数T2は時定数T1より1
0倍大きい範囲にある。
【0027】検出した変調信号の処理、時間平均化及び
比較を含む上記した多くの機能は、マイクロコントロー
ラ内のソフトウエアのステップとして実行できることは
当業者には理解されよう。特許請求の範囲に記載された
本発明は、その範囲にハードウエア及びソフトウエアの
両方の変形例を含む。
比較を含む上記した多くの機能は、マイクロコントロー
ラ内のソフトウエアのステップとして実行できることは
当業者には理解されよう。特許請求の範囲に記載された
本発明は、その範囲にハードウエア及びソフトウエアの
両方の変形例を含む。
【0028】上記実施例では、UHF帯で電気外科用電
力を加えることは、発生器の出力回路の反射或いは逆方
向電力をモニタすることにより制御される。発生器出力
からの反射電力信号が組織乾燥の徴候を示す場合でも、
ある条件下では、組織水分の気化段階を終えるまでUH
F帯或いはより高い周波数で電力を給送し続けることが
有利である。一旦そのような水分が消散したなら、発生
器出力に与えられる負荷インピーダンスを検出すること
により組織の状態をモニタすることが有利である。これ
は、100kHz乃至40MHzの範囲、好ましくは3
00kHz乃至5MHzの範囲のHF/VHF帯で行う
ことが最も望ましい。
力を加えることは、発生器の出力回路の反射或いは逆方
向電力をモニタすることにより制御される。発生器出力
からの反射電力信号が組織乾燥の徴候を示す場合でも、
ある条件下では、組織水分の気化段階を終えるまでUH
F帯或いはより高い周波数で電力を給送し続けることが
有利である。一旦そのような水分が消散したなら、発生
器出力に与えられる負荷インピーダンスを検出すること
により組織の状態をモニタすることが有利である。これ
は、100kHz乃至40MHzの範囲、好ましくは3
00kHz乃至5MHzの範囲のHF/VHF帯で行う
ことが最も望ましい。
【0029】図5を参照すると、このように負荷インピ
ーダンスをモニタすることができる電気外科システム
は、UHF或いはEHF帯の周波数、典型的には2.4
5GHzの信号を給送するための上側周波数源部62
と、HF/VHF帯の周波数、この好ましくは約1MH
zの信号を給送するための下側周波数源部64とを備え
る発生器を有する。図1〜図3を参照して上に記載した
実施形態と同様に、UHF/EHF帯周波数源は、イン
ピーダンスアイソレータ18に加えるために出力14に
UHF/EHF順方向電力信号を生成するUHF/EH
F電力増幅器14を駆動する。アイソレータ18はこの
場合には、コンバイナ回路66を介して発生器出力端子
21に接続される。UHF/EHF周波数源の動作周波
数で負荷から反射される電力は、インピーダンスアイソ
レータ18によりダンプ用負荷22に配向される。
ーダンスをモニタすることができる電気外科システム
は、UHF或いはEHF帯の周波数、典型的には2.4
5GHzの信号を給送するための上側周波数源部62
と、HF/VHF帯の周波数、この好ましくは約1MH
zの信号を給送するための下側周波数源部64とを備え
る発生器を有する。図1〜図3を参照して上に記載した
実施形態と同様に、UHF/EHF帯周波数源は、イン
ピーダンスアイソレータ18に加えるために出力14に
UHF/EHF順方向電力信号を生成するUHF/EH
F電力増幅器14を駆動する。アイソレータ18はこの
場合には、コンバイナ回路66を介して発生器出力端子
21に接続される。UHF/EHF周波数源の動作周波
数で負荷から反射される電力は、インピーダンスアイソ
レータ18によりダンプ用負荷22に配向される。
【0030】周波数源の下側周波数部64は、下側周波
数、すなわち周波数源部64の動作周波数の信号を、電
圧及び電流検出段70及び応答補償段72を介して、コ
ンバイナ66の第2の入力に信号を給送するHF/VH
F電力増幅器68を駆動する。
数、すなわち周波数源部64の動作周波数の信号を、電
圧及び電流検出段70及び応答補償段72を介して、コ
ンバイナ66の第2の入力に信号を給送するHF/VH
F電力増幅器68を駆動する。
【0031】従って、発生器は、それぞれ2.45GH
zと1MHzの上側周波数と下側周波数の両方で出力端
子21に電気外科用電力を供給することができる。上記
のように、電力増幅器14により発生器出力21に給送
される電気外科用信号のレベルは、制御出力16Bを介
して制御システム16により制御される。制御システム
は、電圧及び電流検出段70からのモニタ用信号を受信
するための負荷インピーダンスモニタ用入力16Dを有
し、モニタ用信号は周波数源の下側周波数部64の周波
数で測定される発生器出力21に与えられる負荷インピ
ーダンスを表している。コンバイナ66及び応答補償段
72は、モニタ用信号が、下側周波数のみ、すなわち1
00kHz乃至40MHz帯、或いは300kHz乃至
5MHz帯における負荷インピーダンスの変化に概ね応
答するように動作する。
zと1MHzの上側周波数と下側周波数の両方で出力端
子21に電気外科用電力を供給することができる。上記
のように、電力増幅器14により発生器出力21に給送
される電気外科用信号のレベルは、制御出力16Bを介
して制御システム16により制御される。制御システム
は、電圧及び電流検出段70からのモニタ用信号を受信
するための負荷インピーダンスモニタ用入力16Dを有
し、モニタ用信号は周波数源の下側周波数部64の周波
数で測定される発生器出力21に与えられる負荷インピ
ーダンスを表している。コンバイナ66及び応答補償段
72は、モニタ用信号が、下側周波数のみ、すなわち1
00kHz乃至40MHz帯、或いは300kHz乃至
5MHz帯における負荷インピーダンスの変化に概ね応
答するように動作する。
【0032】動作中に、電圧及び電流検出段70は、下
側周波数における負荷インピーダンスの測定値として用
いることができるモニタ用信号を駆動するために、発生
器出力21に下側周波数で供給される電圧及び電流に関
連する振幅及び位相情報を検出する。このようにして、
例えば検出された下側周波数負荷インピーダンスが、必
要とされる組織の状態を示す所定のレベルに達す場合、
電力増幅器14からの電気外科用電力の給送を調整、低
下或いは遮断することができる。特にこれを用いて、凝
固或いは乾燥の実施時に、治療を組織の凝固或いは乾燥
に制限することができる。言い換えると、必要がない場
合に組織の気化或いは剥離を防ぐことができる。同様
に、インピーダンス或いは抵抗閾値を用いて、組織が気
化する前に予め凝固治療の完了を判定することもでき、
制御システムが、所定の閾値に達した場合に、組織気化
信号を発生器出力端子21に加えるように構成される。
これは、電気外科用電力が上側周波数で支配的に供給さ
れる状態から、電気外科用電力が下側周波数で支配的に
供給される状態に切り替えることにより行うことができ
る。
側周波数における負荷インピーダンスの測定値として用
いることができるモニタ用信号を駆動するために、発生
器出力21に下側周波数で供給される電圧及び電流に関
連する振幅及び位相情報を検出する。このようにして、
例えば検出された下側周波数負荷インピーダンスが、必
要とされる組織の状態を示す所定のレベルに達す場合、
電力増幅器14からの電気外科用電力の給送を調整、低
下或いは遮断することができる。特にこれを用いて、凝
固或いは乾燥の実施時に、治療を組織の凝固或いは乾燥
に制限することができる。言い換えると、必要がない場
合に組織の気化或いは剥離を防ぐことができる。同様
に、インピーダンス或いは抵抗閾値を用いて、組織が気
化する前に予め凝固治療の完了を判定することもでき、
制御システムが、所定の閾値に達した場合に、組織気化
信号を発生器出力端子21に加えるように構成される。
これは、電気外科用電力が上側周波数で支配的に供給さ
れる状態から、電気外科用電力が下側周波数で支配的に
供給される状態に切り替えることにより行うことができ
る。
【0033】ある状況では、無線周波数源の下側周波数
部64の動作周波数を制御できることが有用である。こ
れは、周波数源部64の周波数制御入力に接続される、
制御システムからの周波数制御出力16Eを介して実現
することができる。
部64の動作周波数を制御できることが有用である。こ
れは、周波数源部64の周波数制御入力に接続される、
制御システムからの周波数制御出力16Eを介して実現
することができる。
【0034】ここでインピーダンス検出が行われる方法
が、図6を参照してより詳細に記載されるであろう。こ
こで、下側周波数源部64及び電力増幅器68は、応答
補償段72として動作し、コイル72L及びコンデンサ
72Cを備えるシャント(並列)接続の並列共振回路を
介して、典型的には1MHzの信号を給送する簡単なH
F/VHF電圧源64、68として示される。発生器出
力端子21に取着される電極アセンブリ74、及び治療
中の患者26の組織に起因する下側周波数における負荷
は、それぞれ並列コンデンサ74C、組織の抵抗76及
び直列に結合する容量78により表される。下側周波数
電圧及び電流信号は、周波数源64、68の出力ライン
の1つに並列に接続される電圧検出トランス80と、そ
の出力ラインの1つに直列に接続される電流検出トラン
ス82とをそれぞれ用いて、取り出される。これらのト
ランス80、82は、信号調整段84の各入力端子対に
接続される2次巻線を有し、信号調整段84が、電圧振
幅、電流振幅及び電圧信号と電流信号との位相差(φ)
を表す出力84A、84B及び84Cに3つの出力信号
を生成する。
が、図6を参照してより詳細に記載されるであろう。こ
こで、下側周波数源部64及び電力増幅器68は、応答
補償段72として動作し、コイル72L及びコンデンサ
72Cを備えるシャント(並列)接続の並列共振回路を
介して、典型的には1MHzの信号を給送する簡単なH
F/VHF電圧源64、68として示される。発生器出
力端子21に取着される電極アセンブリ74、及び治療
中の患者26の組織に起因する下側周波数における負荷
は、それぞれ並列コンデンサ74C、組織の抵抗76及
び直列に結合する容量78により表される。下側周波数
電圧及び電流信号は、周波数源64、68の出力ライン
の1つに並列に接続される電圧検出トランス80と、そ
の出力ラインの1つに直列に接続される電流検出トラン
ス82とをそれぞれ用いて、取り出される。これらのト
ランス80、82は、信号調整段84の各入力端子対に
接続される2次巻線を有し、信号調整段84が、電圧振
幅、電流振幅及び電圧信号と電流信号との位相差(φ)
を表す出力84A、84B及び84Cに3つの出力信号
を生成する。
【0035】制御システム16は低周波数検出入力16
Dでこれらの信号を受信し、電圧振幅及び電流振幅(V
I)と、式V/(Icosφ)に従う位相差φとを結合
することにより、負荷インピーダンス(それゆえ組織の
インピーダンス)を計算する。この計算は出力端子16
PAを有する計算段16Pとして図6に示されており、
出力端子16PAはコンパレータモジュール16Qを駆
動し、さらにコンパレータモジュール16Qが出力増幅
器16Rを駆動する。コンパレータ16Qは、出力増幅
器16Rが検出されたインピーダンスとインピーダンス
基準値との間の差に比例する出力を生成するように、組
織インピーダンス或いは抵抗閾値を表す信号を基準信号
として受信し、増幅器16Rは、検出されたインピーダ
ンスが所定の閾値に達する場合に、電力増幅器14(図
5参照)から給送される電力が上限値から折り返され
る、言い換えると上限値から減少するように、電力上限
値を表す基準信号を受信する第2の入力を備えている。
Dでこれらの信号を受信し、電圧振幅及び電流振幅(V
I)と、式V/(Icosφ)に従う位相差φとを結合
することにより、負荷インピーダンス(それゆえ組織の
インピーダンス)を計算する。この計算は出力端子16
PAを有する計算段16Pとして図6に示されており、
出力端子16PAはコンパレータモジュール16Qを駆
動し、さらにコンパレータモジュール16Qが出力増幅
器16Rを駆動する。コンパレータ16Qは、出力増幅
器16Rが検出されたインピーダンスとインピーダンス
基準値との間の差に比例する出力を生成するように、組
織インピーダンス或いは抵抗閾値を表す信号を基準信号
として受信し、増幅器16Rは、検出されたインピーダ
ンスが所定の閾値に達する場合に、電力増幅器14(図
5参照)から給送される電力が上限値から折り返され
る、言い換えると上限値から減少するように、電力上限
値を表す基準信号を受信する第2の入力を備えている。
【0036】別の制御動作は、例えば、所与の組織のイ
ンピーダンスに達する際に、UHF/EHF電力の給送
が完全に停止できるようすることにより実施することも
できる。
ンピーダンスに達する際に、UHF/EHF電力の給送
が完全に停止できるようすることにより実施することも
できる。
【0037】下側周波数におけるインピーダンス検出
は、電気外科的な効果を生じるのに十分なレベルの下側
周波数信号を(周波数源64、68において)生成する
ことなく実行できることは理解されよう。従って、下側
周波数での治療が必要ない場合、下側周波数信号は、単
にインピーダンス検出を実行できるだけの十分なレベル
で供給され、トランス80、82及び信号調整段84
が、適切に検出できるように構成される。組織への効果
ではなく、単に測定のために十分なレベルで下側周波数
の無線周波数信号を給送することにより、接地漏れを防
ぐ必要がなくなる。
は、電気外科的な効果を生じるのに十分なレベルの下側
周波数信号を(周波数源64、68において)生成する
ことなく実行できることは理解されよう。従って、下側
周波数での治療が必要ない場合、下側周波数信号は、単
にインピーダンス検出を実行できるだけの十分なレベル
で供給され、トランス80、82及び信号調整段84
が、適切に検出できるように構成される。組織への効果
ではなく、単に測定のために十分なレベルで下側周波数
の無線周波数信号を給送することにより、接地漏れを防
ぐ必要がなくなる。
【0038】図5は図1乃至図3を参照して上に記載さ
れるような反射電力に応じるUHF/EHF電力出力の
制御を示していないが、図5の発生器は両方の検出機能
を実行するための機構を有しており、反射電力検出段は
単に明瞭に示すために省略されていることは理解されよ
う。しかしながら下側周波数インピーダンス検出のみを
用いるシステム及び発生器も、その態様の少なくとも1
つに従えば、本発明の範囲内に入る。
れるような反射電力に応じるUHF/EHF電力出力の
制御を示していないが、図5の発生器は両方の検出機能
を実行するための機構を有しており、反射電力検出段は
単に明瞭に示すために省略されていることは理解されよ
う。しかしながら下側周波数インピーダンス検出のみを
用いるシステム及び発生器も、その態様の少なくとも1
つに従えば、本発明の範囲内に入る。
【0039】組織のインピーダンス或いは抵抗が組織凝
固及び乾燥中に時間とともに変動する方法は、米国特許
第5,423,810号に示されており、その内容はこ
こで参照して本明細書の一部としている。
固及び乾燥中に時間とともに変動する方法は、米国特許
第5,423,810号に示されており、その内容はこ
こで参照して本明細書の一部としている。
【0040】また同出願人による英国特許出願第GB2
214430A号に記載されるように、その出力周波数
が負荷インピーダンスに依存するという点で自己同調す
る可変周波数電力発振器として、発生器の下側周波数部
を構成することもできる。この場合には、発振器周波数
は、インピーダンスを表すモニタ用信号として用いるこ
とができ、発生器は、周波数源64、68の出力に接続
される周波数カウンタ或いは別の周波数応答回路を用い
るインピーダンス検出段を備える。
214430A号に記載されるように、その出力周波数
が負荷インピーダンスに依存するという点で自己同調す
る可変周波数電力発振器として、発生器の下側周波数部
を構成することもできる。この場合には、発振器周波数
は、インピーダンスを表すモニタ用信号として用いるこ
とができ、発生器は、周波数源64、68の出力に接続
される周波数カウンタ或いは別の周波数応答回路を用い
るインピーダンス検出段を備える。
【0041】図1乃至図3を参照して上に記載した実施
例と同様に、その制御システム16、及び含まれる周波
数によっては信号調整段84の一部はマイクロコントロ
ーラ内のソフトウエアステップとして実装することもで
きる。
例と同様に、その制御システム16、及び含まれる周波
数によっては信号調整段84の一部はマイクロコントロ
ーラ内のソフトウエアステップとして実装することもで
きる。
【図1】本発明による電気外科用信号発生器をそれぞれ
含む電気外科システムの第1の実施形態のブロック図で
ある。
含む電気外科システムの第1の実施形態のブロック図で
ある。
【図2】本発明による電気外科用信号発生器をそれぞれ
含む電気外科システムの第2の実施形態のブロック図で
ある。
含む電気外科システムの第2の実施形態のブロック図で
ある。
【図3】本発明による電気外科用信号発生器をそれぞれ
含む電気外科システムの第3の実施形態のブロック図で
ある。
含む電気外科システムの第3の実施形態のブロック図で
ある。
【図4】A乃至Cよりなり、それぞれ図1、図2及び図
3の発生器用の別の検出器及び信号調整段を示すブロッ
ク図である。
3の発生器用の別の検出器及び信号調整段を示すブロッ
ク図である。
【図5】本発明による電気外科システムの第4の実施形
態のブロック図である。
態のブロック図である。
【図6】図5のシステムの一部をより詳細に示すブロッ
ク図及び回路図である。
ク図及び回路図である。
10 発生器 12 周波数発生源 14 電力増幅器 14A 電力増幅器出力 16 制御システム 16A モニタ用入力 16B 制御出力 16D モニタ用入力 16E 周波数制御出力 16P 計算段 16PA 計算段出力 16Q コンパレータモジュール 16R 出力増幅器 18 アイソレータ 20 出力ライン 21 発生器出力端子 22 ダンプ用負荷 23 方向性結合器 23´ 方向性結合器 23A 逆方向電力出力 23A´ 逆方向電力出力 24 電極アセンブリ 26 患者 28 検出回路 29 検出器及び信号調整段 30 電力減衰器 40 検出器 40A 検出器出力 44 コンパレータ 46 時間平均化モジュール 50 微分器モジュール 54 平均化回路 56 平均化回路 62 上側周波数発生部 64 下側周波数発生部 66 コンバイナ回路 68 電力増幅器 70 電圧及び電流検出段 72 応答補償段 72L コイル 72C コンデンサ 74 電極アセンブリ 74C コンデンサ 76 組織の抵抗 78 組織の容量 80 電圧検出トランス 82 電圧検出トランス 84 信号調整段 84A 電圧振幅 84B 電流振幅 84C 電圧電流位相差
───────────────────────────────────────────────────── フロントページの続き (72)発明者 クリストファー・ポール・ハンコック イギリス国、ウェールズ、カーディフ・シ ーエフ2・3イーエックス、コトレル・ロ ード 128 (72)発明者 キース・ペニー イギリス国、モンマス・エヌピー5・4エ ルユー、アッパー・レッドブルック、ウッ ドランズ (72)発明者 フランシス・アモアー イギリス国、カーディフ・シーエフ14・1 ティイー、ウィッチャーチ、グリーンフィ ールド・ロード 36 (72)発明者 コリン・チャールズ・オウエン・ゴブル イギリス国、ウェールズ、サウス・グラー モーガン・シーエフ64・1エイティ、ピナ ース、クリブ・クレセント、オズボーン・ ハウス 5
Claims (24)
- 【請求項1】 電気外科用信号発生器において、 電気外科用電極アセンブリに接続するための前記発生器
の出力に接続される無線周波数(RF)電力源と、 前記出力からフィードバックされた反射電力の変化を検
出するように動作する検出回路と、 前記検出回路からのモニタ用信号を処理するために該検
出回路に接続される入力と、前記電力源の電力出力を調
整するために前記電力源に接続される電力制御出力とを
備える制御装置と、 を備え、 前記制御装置が、治療中の組織の状態の変化に起因する
反射電力の変化を示す前記モニタ用信号の所定の状態に
応答して、前記電力源から前記発生器出力への無線周波
数信号の適用を低減或いは停止するように構成されるこ
とを特徴とする電気外科用信号発生器。 - 【請求項2】 前記無線周波数電力源は300MHz以
上で動作するように構成され、前記検出回路は、前記無
線周波数電力源と前記発生器出力との間にある出力ライ
ンに関連し、前記発生器出力から反射されて戻った電力
を表す電圧或いは電流信号を与えるための反射電力出力
を有する方向性結合器を備えることを特徴とする請求項
1に記載の発生器。 - 【請求項3】 前記無線周波数電力源は300MHz以
上で動作するように構成され、前記発生器は、前記電力
源と前記発生器出力との間にある出力ラインに接続され
るインピーダンスアイソレータを備え、前記検出回路は
前記インピーダンスアイソレータの反射電力出力に接続
される入力を有することを特徴とする請求項1に記載の
発生器。 - 【請求項4】 前記検出回路は、前記反射電力の変化の
速度の関数として前記モニタ信号を生成するように構成
されることを特徴とする請求項1または2に記載の発生
器。 - 【請求項5】 前記検出回路は前記発生器出力に前記電
力源を接続する出力ラインに関連し、前記発生器出力か
ら反射された電力を表す電圧或いは電流信号である反射
電力信号を生成するように構成され、また前記検出回路
は、前記反射電力信号の相対的に遅い変化を補償して、
概ね前記反射電力信号の相対的に急速な変化の関数であ
る信号として前記モニタ用信号を生成するように構成さ
れる信号調整段を備えることを特徴とする請求項1乃至
4のいずれか一項に記載の発生器。 - 【請求項6】 前記信号調整段は、コンパレータに給送
するデュアルチャネル装置を備え、前記チャネルの1つ
は他のチャネルに関連する時定数より長い時定数を有す
る平均化素子を備え、各チャネルは前記コンパレータの
各入力に給送し、前記モニタ用信号が前記コンパレータ
の出力から得られることを特徴とする請求項1に記載の
発生器。 - 【請求項7】 前記検出回路は、反射電力信号の変調を
復調するための復調器を備えることを特徴とする請求項
1または2に記載の発生器。 - 【請求項8】 前記復調器は振幅復調器であることを特
徴とする請求項6に記載の発生器。 - 【請求項9】 前記検出回路は、 前記電力源を前記発生器出力に接続する出力ラインに関
連する第1の部分であって、該第1の部分が、前記発生
器出力から反射された電力を表す電圧或いは電流信号で
ある反射電力信号を生成するように構成される第1の部
分と、 前記第1の部分に接続され、前記反射電力信号の変調を
検出するための検出器の形をとり、振幅、位相或いは周
波数のような前記変調の所定の特性の関数である検出信
号を生成するように構成される第2の部分と、 概ね前記変調特性の相対的に速い変化の関数である信号
として前記モニタ信号を生成するために、前記変調特性
の相対的に遅い変化を補償するように構成される信号調
整段を備える第3の部分と、 を備えることを特徴とする請求項6または7に記載の発
生器。 - 【請求項10】 前記信号調整段は、コンパレータに給
送するデュアルチャネル装置を備え、前記チャネルの1
つが他のチャネルに関連する時定数より長い時定数を有
する平均化素子を備え、各チャネルが前記コンパレータ
の各入力に給送し、前記モニタ用信号が前記コンパレー
タの出力から得られることを特徴とする請求項8に記載
の発生器。 - 【請求項11】 前記検出回路及び前記制御装置は、前
記検出信号により表されるような前記変調が所定の閾値
レベルより大きい変調特性を有する場合、前記電力源の
出力電力を低下させるように構成されることを特徴とす
る請求項6乃至9のいずれか一項に記載の発生器。 - 【請求項12】 前記検出回路及び前記制御装置は、前
記変調特性が所定の閾値レベルより大きい時間の後に、
前記検出信号により表されるような前記変調が実質的に
停止する場合、前記電力源の出力電力を低下させるよう
に構成されることを特徴とする請求項6乃至9のいずれ
か一項に記載の発生器。 - 【請求項13】 前記変調特性は振幅変調であることを
特徴とする請求項10または11に記載の発生器。 - 【請求項14】 前記電力源は300MHz以上で動作
可能な上側周波数部と、300MHz未満で動作可能な
下側周波数部とを備え、両方の周波数部が前記発生器出
力に接続され、前記検出回路が、前記電力源の前記下側
周波数部の動作周波数(単数または複数)で負荷インピ
ーダンスを検出するための負荷インピーダンスセンサを
備え、前記制御装置が、前記電力源の前記下側周波数部
の前記動作周波数(単数または複数)で検出された所定
の負荷インピーダンス状態に応じて、前記電力源の前記
上側周波数部からの前記無線周波数の適用を減少或いは
停止するように構成されることを特徴とする請求項1乃
至13のいずれか一項に記載の発生器。 - 【請求項15】 前記負荷インピーダンスセンサは、前
記電力源の前記下側周波数部と前記発生器出力との間に
ある出力ラインに接続される出力電圧及び電流測定回路
を備えることを特徴とする請求項14に記載の発生器。 - 【請求項16】 前記電力源の前記下側周波数部の前記
動作周波数は負荷インピーダンスに依存し、前記負荷イ
ンピーダンスセンサは前記下側周波数部の前記周波数を
検出することを特徴とする請求項14に記載の発生器。 - 【請求項17】 前記制御装置は、前記検出された負荷
インピーダンスが所定の閾値より大きい場合、前記電力
源の前記上側周波数部からの電力の適用を減少或いは停
止するように構成されることを特徴とする請求項14乃
至16のいずれか一項に記載の発生器。 - 【請求項18】 前記電力源の前記下側周波数部と前記
インピーダンスセンサとは、インピーダンス検出が、無
視し得る電気外科的効果を有するほど十分に低いレベル
からなる信号を前記発生器出力に適用することにより実
行されることができるように構成され、前記下側周波数
部の前記動作周波数(単数または複数)は100kHz
から40MHzの範囲にあることを特徴とする請求項1
4乃至17のいずれか一項に記載の発生器。 - 【請求項19】 電気外科用信号発生器であって、 300MHz以上で動作可能な上側周波数部と300M
Hz未満で動作可能な下側周波数部とを有する無線周波
数(RF)電力源と、 電気外科用電極アセンブリに接続するための発生器出力
であって、前記電力源の前記両方の周波数部が前記出力
に接続される発生器出力と、 前記電力源の前記下側周波数部の動作周波数(単数また
は複数)で負荷インピーダンスを検出するための負荷イ
ンピーダンスセンサを備える検出回路と、 前記検出回路からのモニタ用信号を処理するために前記
検出回路に接続される入力と、前記電力源の前記電力出
力を調整するために前記電力源に接続される電力制御出
力とを有する制御装置と、 を備え、 前記制御装置が、前記電力源の前記下側周波数部の前記
動作周波数(単数または複数)で検出される負荷インピ
ーダンスの変化を示す前記モニタ用信号の所定の状態に
応じて、前記電力源の前記上側周波数部から前記発生器
出力への無線周波数信号の適用を減少或いは停止するよ
うに構成されることを特徴とする電気外科用信号発生
器。 - 【請求項20】 前記負荷インピーダンスセンサは、前
記電力源の前記下側周波数部と前記発生器出力との間に
ある出力ラインに接続される出力電圧及び電流測定回路
を備えることを特徴とする請求項19に記載の発生器。 - 【請求項21】 前記電力源の前記下側周波数部の前記
動作周波数は負荷インピーダンスに依存し、前記負荷イ
ンピーダンスセンサが前記下側周波数部の周波数を検出
することを特徴とする請求項19に記載の発生器。 - 【請求項22】 前記制御装置は、前記検出された負荷
インピーダンスが所定の閾値より大きくなる場合、前記
電力源の前記上側周波数部からの電力の適用を減少或い
は停止するように構成されることを特徴とする請求項1
9乃至21のいずれか一項に記載の発生器。 - 【請求項23】 前記電力源の前記下側周波数部と前記
インピーダンスセンサとは、インピーダンス検出が、無
視し得る電気外科的効果を有するほど十分に低いレベル
からなる信号を前記発生器出力に適用することにより実
行されることができるように構成され、前記下側周波数
部の前記動作周波数(単数または複数)は100kHz
から40MHzの範囲にあることを特徴とする請求項1
9乃至22のいずれか一項に記載の発生器。 - 【請求項24】 請求項1乃至23のいずれか一項に記
載の電気外科用信号発生器を備え、発生器出力に接続さ
れる電気外科システムであって、電極アセンブリが組織
治療電極を備えることを特徴とする電気外科システム。
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GB9913652.5 | 1999-06-11 | ||
GBGB9913652.5A GB9913652D0 (en) | 1999-06-11 | 1999-06-11 | An electrosurgical generator |
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Family
ID=10855198
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Also Published As
Publication number | Publication date |
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EP1080694A1 (en) | 2001-03-07 |
GB9913652D0 (en) | 1999-08-11 |
AU3939900A (en) | 2000-12-14 |
CA2308931A1 (en) | 2000-12-11 |
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