JP2001008944A - 電気外科用信号発生器及び電気外科システム - Google Patents
電気外科用信号発生器及び電気外科システムInfo
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- 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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- 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
- A61B2018/1293—Generators therefor having means to prevent interference
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Abstract
(57)【要約】
【課題】 電気外科システムの効率を改善することであ
る。 【解決手段】 特にUHF或いはより高い周波数で動作
できる電気外科用信号発生器は、反射電力を検出するた
めの回路32と、発生器の無線周波数出力の周波数が、
反射電力をモニタしながら変更されるようにするため
に、検出回路に接続される制御装置とを備える。その後
その出力周波数は、最小の反射電力レベルに対応する値
に設定される。
る。 【解決手段】 特にUHF或いはより高い周波数で動作
できる電気外科用信号発生器は、反射電力を検出するた
めの回路32と、発生器の無線周波数出力の周波数が、
反射電力をモニタしながら変更されるようにするため
に、検出回路に接続される制御装置とを備える。その後
その出力周波数は、最小の反射電力レベルに対応する値
に設定される。
Description
【0001】
【発明の属する技術分野】この発明は電気外科用信号発
生器及び電気外科用信号発生器を組み込んだ電気外科シ
ステムに関し、詳細には電気外科用電力が可変周波数で
送給される発生器及びシステムに関する。
生器及び電気外科用信号発生器を組み込んだ電気外科シ
ステムに関し、詳細には電気外科用電力が可変周波数で
送給される発生器及びシステムに関する。
【0002】
【従来の技術】電気外科用信号発生器に接続される電極
アセンブリを備えた電気外科システムの性能は、無線周
波数電力が治療中の組織に結合することができる効率
と、治療電極の末端で生成することができる電圧及び電
流とに関連する。
アセンブリを備えた電気外科システムの性能は、無線周
波数電力が治療中の組織に結合することができる効率
と、治療電極の末端で生成することができる電圧及び電
流とに関連する。
【0003】治療電極に与えられる電気的負荷は、電力
が電極に供給される周波数と、電極の構成と、電極の動
作モードと、電解質のような治療中の組織に関連する他
の材料の組織の性質と、手術中の電極の位置と、外科器
具または隣接する身体構造のような他の物体の存在とを
含むいくつかの変数に依存する。これらの要因により負
荷インピーダンスはアプリケーションの関数として、さ
らに時間の関数として変化するようになるが、それは主
に治療中の組織の電気的特性及び隣接して存在する物質
並びに物体の電気的特性が手術の結果として変化するた
めである。負荷インピーダンスが変化するそのような状
況では、効率も広範に変動する。効率は多くの場合、治
療電極に与えられた電気的負荷に最大電力が送給される
際に、最大になるものと判断される。最大電力の送給
は、その負荷が、電気外科システム(すなわち発生器及
び電極アセンブリ)の駆動インピーダンスに共役なイン
ピーダンスに整合する際に実現される。
が電極に供給される周波数と、電極の構成と、電極の動
作モードと、電解質のような治療中の組織に関連する他
の材料の組織の性質と、手術中の電極の位置と、外科器
具または隣接する身体構造のような他の物体の存在とを
含むいくつかの変数に依存する。これらの要因により負
荷インピーダンスはアプリケーションの関数として、さ
らに時間の関数として変化するようになるが、それは主
に治療中の組織の電気的特性及び隣接して存在する物質
並びに物体の電気的特性が手術の結果として変化するた
めである。負荷インピーダンスが変化するそのような状
況では、効率も広範に変動する。効率は多くの場合、治
療電極に与えられた電気的負荷に最大電力が送給される
際に、最大になるものと判断される。最大電力の送給
は、その負荷が、電気外科システム(すなわち発生器及
び電極アセンブリ)の駆動インピーダンスに共役なイン
ピーダンスに整合する際に実現される。
【0004】動作の周波数が高くなるに従って、特に発
生器がUHF帯で電気外科用電力を送給するように構成
された場合、最大電力を送給できるか否かは、発生器周
波数が好ましい動作周波数付近にとどまるか否かによっ
て決まる。この好適な周波数或いは関連する狭い周波数
範囲は、製造誤差、及び保管並びに電極使用に起因する
経時変化により電極毎に変動する。これらがさらに別の
要因となり、それゆえ電気外科の効率に影響を与える。
生器がUHF帯で電気外科用電力を送給するように構成
された場合、最大電力を送給できるか否かは、発生器周
波数が好ましい動作周波数付近にとどまるか否かによっ
て決まる。この好適な周波数或いは関連する狭い周波数
範囲は、製造誤差、及び保管並びに電極使用に起因する
経時変化により電極毎に変動する。これらがさらに別の
要因となり、それゆえ電気外科の効率に影響を与える。
【0005】
【発明が解決しようとする課題】従ってこの発明の目的
は、電気外科システムの効率を改善することである。
は、電気外科システムの効率を改善することである。
【0006】
【課題を解決するための手段】従ってこの発明の一態様
は、電気外科用信号発生器の動作の周波数を自動調整す
ることによる電気外科システムの性能の最適化である。
これは、電極性能を最適化するために発生器内の周波数
源の周波数を調整する制御システムにおいて、反射した
電力信号を解析することにより行われる。詳細にはこの
発明は、可変周波数無線周波数源と、反射電力検出回路
と、検出回路及び周波数源に接続される制御装置とを備
えた電気外科用信号発生器を提供し、制御装置は、反射
した電力を示す検出回路から反射電力出力信号を受信し
て、周波数源の周波数を変化させ、また周波数源の周波
数を相対的に低い反射電力レベルに対応する値に設定す
るように構成される。周波数は、一般に最大限に送給さ
れる電気外科用電力と相関がある反射電力信号の大きさ
を最小にするように調整されることが好ましい。従って
好適な発生器では、制御装置が、定期的に周波数源が複
数の異なる選択された試験周波数を生成できるように
し、各試験周波数において出力信号をモニタし、その後
その周波数源を概ね最小の反射電力に対応する動作周波
数に設定するように構成される。
は、電気外科用信号発生器の動作の周波数を自動調整す
ることによる電気外科システムの性能の最適化である。
これは、電極性能を最適化するために発生器内の周波数
源の周波数を調整する制御システムにおいて、反射した
電力信号を解析することにより行われる。詳細にはこの
発明は、可変周波数無線周波数源と、反射電力検出回路
と、検出回路及び周波数源に接続される制御装置とを備
えた電気外科用信号発生器を提供し、制御装置は、反射
した電力を示す検出回路から反射電力出力信号を受信し
て、周波数源の周波数を変化させ、また周波数源の周波
数を相対的に低い反射電力レベルに対応する値に設定す
るように構成される。周波数は、一般に最大限に送給さ
れる電気外科用電力と相関がある反射電力信号の大きさ
を最小にするように調整されることが好ましい。従って
好適な発生器では、制御装置が、定期的に周波数源が複
数の異なる選択された試験周波数を生成できるように
し、各試験周波数において出力信号をモニタし、その後
その周波数源を概ね最小の反射電力に対応する動作周波
数に設定するように構成される。
【0007】このようにして、動作周波数を自動的に調
整することにより性能が最適化され、それにより上記要
因に起因する負荷インピーダンスの変化を考慮し、結果
的にコストの削減とともに電極製造誤差を緩和すること
ができる。
整することにより性能が最適化され、それにより上記要
因に起因する負荷インピーダンスの変化を考慮し、結果
的にコストの削減とともに電極製造誤差を緩和すること
ができる。
【0008】検出回路は、発生器の出力段、すなわち出
力段と電極に接続するための発生器の出力端子との間に
ある電力出力ラインに関連する電圧或いは電流モニタを
備えることができる。典型的には、電圧或いは電流モニ
タは、出力ライン内にハイブリッド結合器或いはサーキ
ュレータを備える。検出回路により生成される電圧或い
は電流の振幅及び位相のいずれか、或いはいずれも、発
生器の出力端子に接続される電極に与えられるインピー
ダンスの測定値を表し、それゆえそのような振幅或いは
位相が電力送給効率の測定値を構成する。
力段と電極に接続するための発生器の出力端子との間に
ある電力出力ラインに関連する電圧或いは電流モニタを
備えることができる。典型的には、電圧或いは電流モニ
タは、出力ライン内にハイブリッド結合器或いはサーキ
ュレータを備える。検出回路により生成される電圧或い
は電流の振幅及び位相のいずれか、或いはいずれも、発
生器の出力端子に接続される電極に与えられるインピー
ダンスの測定値を表し、それゆえそのような振幅或いは
位相が電力送給効率の測定値を構成する。
【0009】戻り信号の大きさを連続して、或いは定期
的にモニタすることにより、最大電力送給のために周波
数源の周波数を連続して、或いは定期的に調整できるよ
うになる。実際に、戻り信号が増加した反射電力のしる
しとしての基準閾値と連続して比較され、周波数源に対
する周波数の変更をトリガし、制御装置が新しい周波数
の反射電力レベルをモニタし、効率を高めるために正確
な方向に周波数が調整されたか否かを判定する。
的にモニタすることにより、最大電力送給のために周波
数源の周波数を連続して、或いは定期的に調整できるよ
うになる。実際に、戻り信号が増加した反射電力のしる
しとしての基準閾値と連続して比較され、周波数源に対
する周波数の変更をトリガし、制御装置が新しい周波数
の反射電力レベルをモニタし、効率を高めるために正確
な方向に周波数が調整されたか否かを判定する。
【0010】別法では、制御装置は定期的に試験シーケ
ンスを実行するように構成され、そのシーケンスにおい
て、周波数源の周波数が所定の範囲(最初に最大範囲
内、次に縮小した範囲内)に渡って変化し、その際出力
信号がモニタされる。後続の治療段階では、制御装置が
周波数源を動作周波数に設定するように構成され、動作
周波数は、その試験シーケンス中のモニタされた出力信
号に基づいて、最大送給出力電力が得られる周波数に対
応するように選択される。試験シーケンスは、少なくと
も毎秒2回の割合で、0.2〜5%のデューティサイク
ルで繰返し実行されることができる。
ンスを実行するように構成され、そのシーケンスにおい
て、周波数源の周波数が所定の範囲(最初に最大範囲
内、次に縮小した範囲内)に渡って変化し、その際出力
信号がモニタされる。後続の治療段階では、制御装置が
周波数源を動作周波数に設定するように構成され、動作
周波数は、その試験シーケンス中のモニタされた出力信
号に基づいて、最大送給出力電力が得られる周波数に対
応するように選択される。試験シーケンスは、少なくと
も毎秒2回の割合で、0.2〜5%のデューティサイク
ルで繰返し実行されることができる。
【0011】無線周波数干渉が支障をもたらすと予想さ
れる場合には、周波数源は、試験シーケンス中、処理段
階中の電力よりも低い電力設定で電気外科用電力を送給
するように構成される。
れる場合には、周波数源は、試験シーケンス中、処理段
階中の電力よりも低い電力設定で電気外科用電力を送給
するように構成される。
【0012】別の実施例では、周波数は異なる周波数間
で切り替えられてもよく、組織への電力送給を増加する
ために必要な周波数調整の方向を判定する。このプロセ
スは、それ以上の改善が得られなくなるまで、或いは送
給される電力が再び減少し始めるまで、双方向ベースで
繰返して継続することができ、減少し始める場合には周
波数変化の方向が反転される。最大限に電力を送給する
ための周波数が達成される場合、制御装置が、最適な周
波数の周囲で周波数源の周波数を繰返し切り替えるよう
動作するようにして、連続してこのプロセスを実行する
ことができる。
で切り替えられてもよく、組織への電力送給を増加する
ために必要な周波数調整の方向を判定する。このプロセ
スは、それ以上の改善が得られなくなるまで、或いは送
給される電力が再び減少し始めるまで、双方向ベースで
繰返して継続することができ、減少し始める場合には周
波数変化の方向が反転される。最大限に電力を送給する
ための周波数が達成される場合、制御装置が、最適な周
波数の周囲で周波数源の周波数を繰返し切り替えるよう
動作するようにして、連続してこのプロセスを実行する
ことができる。
【0013】さらに別の実施例では、発生器は、無線周
波数源に接続され、少なくとも2つの異なる周波数成分
を含むように周波数源出力信号を変調するように構成さ
れた変調器を備えることができる。この例では、発生器
は、検出回路の一部を形成しかつその成分周波数での反
射電力の相対的な大きさを示す反射電力出力信号を与え
るように構成された検出器を有していてもよく、制御装
置がこれらの大きさをモニタするように構成され、それ
により送給される電気外科用電力を増加するために必要
とされる周波数調整の方向を判定する。変調は所定の変
調周波数における振幅変調であることが好ましく、変調
の深さは、搬送波(動作の中心周波数)と、その搬送波
周波数のそれぞれ上下に位置する2つの側波帯との間に
電力を分散するように選択される。最適な電気外科の効
率では、2つの側波帯の反射電力レベルは概ね等しくな
る。最適でない周波数では、2つの側波帯成分の反射電
力の振幅は異なり、効率を改善するために周波数源の周
波数が調整されるべき方向を判定するために制御装置に
より処理されることができる。
波数源に接続され、少なくとも2つの異なる周波数成分
を含むように周波数源出力信号を変調するように構成さ
れた変調器を備えることができる。この例では、発生器
は、検出回路の一部を形成しかつその成分周波数での反
射電力の相対的な大きさを示す反射電力出力信号を与え
るように構成された検出器を有していてもよく、制御装
置がこれらの大きさをモニタするように構成され、それ
により送給される電気外科用電力を増加するために必要
とされる周波数調整の方向を判定する。変調は所定の変
調周波数における振幅変調であることが好ましく、変調
の深さは、搬送波(動作の中心周波数)と、その搬送波
周波数のそれぞれ上下に位置する2つの側波帯との間に
電力を分散するように選択される。最適な電気外科の効
率では、2つの側波帯の反射電力レベルは概ね等しくな
る。最適でない周波数では、2つの側波帯成分の反射電
力の振幅は異なり、効率を改善するために周波数源の周
波数が調整されるべき方向を判定するために制御装置に
より処理されることができる。
【0014】発生器は、例えば無線受信アンテナに接続
される放射モニタ信号を受信するための入力を備え、受
信アンテナは、治療中の患者の近く、典型的には数メー
トル以内に、無線干渉をモニタする手段として配置され
る。制御装置はこの場合には、モニタ信号を処理し、干
渉電力閾値を超える場合のような放射モニタ信号の所定
の特性に応じて周波数源を調整するように構成すること
ができる。その後制御装置は、干渉を減少するように所
定の特性に応じて周波数源の周波数を調整するために動
作することができる。
される放射モニタ信号を受信するための入力を備え、受
信アンテナは、治療中の患者の近く、典型的には数メー
トル以内に、無線干渉をモニタする手段として配置され
る。制御装置はこの場合には、モニタ信号を処理し、干
渉電力閾値を超える場合のような放射モニタ信号の所定
の特性に応じて周波数源を調整するように構成すること
ができる。その後制御装置は、干渉を減少するように所
定の特性に応じて周波数源の周波数を調整するために動
作することができる。
【0015】周波数源自体に関しては、周波数源は、連
続した、或いは離散した周波数の範囲或いは周波数の帯
域に渡る周波数において調整することができる。
続した、或いは離散した周波数の範囲或いは周波数の帯
域に渡る周波数において調整することができる。
【0016】またこの発明は、上記のような発生器を含
み、その発生器が、その発生器の出力に接続された少な
くとも1つの治療電極を含む電極アセンブリに接続され
た電気外科システムも提供する。
み、その発生器が、その発生器の出力に接続された少な
くとも1つの治療電極を含む電極アセンブリに接続され
た電気外科システムも提供する。
【0017】この発明の一方法態様によれば、電気外科
システムを動作させる方法は、複数の周波数における無
線周波数源から電気外科用無線周波数電力を送給する過
程と、異なる周波数において反射電力をモニタする過程
と、周波数源が動作する他の周波数に関連する反射電力
レベルより低い反射電力レベルに関連する動作周波数を
設定するように周波数源の周波数を調整する過程とを有
する。
システムを動作させる方法は、複数の周波数における無
線周波数源から電気外科用無線周波数電力を送給する過
程と、異なる周波数において反射電力をモニタする過程
と、周波数源が動作する他の周波数に関連する反射電力
レベルより低い反射電力レベルに関連する動作周波数を
設定するように周波数源の周波数を調整する過程とを有
する。
【0018】以下、この発明の実施の形態について図面
を参照しながら説明する。
を参照しながら説明する。
【0019】
【発明の実施の形態】図1を参照すると、この発明によ
る発生器10は、発振器12と電力増幅器14とを備え
た可変無線周波数源を有する。発振器12は、発振器に
接続され、発振器出力の周波数分周サンプルと比較する
ために、基準周波数源18から基準周波数信号を受信す
るように構成されたデジタル位相同期ループ16を備え
た周波数シンセサイザの一部を形成する。制御装置20
は、位相同期ループに(例えばその分周比を変更するた
めに)、かつ発振器12の周波数を変更するために、制
御信号を(周波数分周器も含む)基準周波数源18に供
給するように構成される。また装置20は、発生器の公
称出力電力を調整するために電力増幅器14に電力制御
出力も供給する。
る発生器10は、発振器12と電力増幅器14とを備え
た可変無線周波数源を有する。発振器12は、発振器に
接続され、発振器出力の周波数分周サンプルと比較する
ために、基準周波数源18から基準周波数信号を受信す
るように構成されたデジタル位相同期ループ16を備え
た周波数シンセサイザの一部を形成する。制御装置20
は、位相同期ループに(例えばその分周比を変更するた
めに)、かつ発振器12の周波数を変更するために、制
御信号を(周波数分周器も含む)基準周波数源18に供
給するように構成される。また装置20は、発生器の公
称出力電力を調整するために電力増幅器14に電力制御
出力も供給する。
【0020】負帰還方式を用いて連続的に精細な周波数
調整を行うために、周波数源の周波数の(デジタルより
もむしろ)アナログ制御を用いることができる。
調整を行うために、周波数源の周波数の(デジタルより
もむしろ)アナログ制御を用いることができる。
【0021】例えば発振器12は電圧制御発振器であ
り、それにより周波数を制御電圧により確定することも
できる。この電圧は、コンデンサに給電する電流生成源
により生成することもできる。制御装置は、それぞれ動
作周波数の増加或いは減少(発振器の設計によっては、
それぞれ減少或いは増加)のいずれが必要とされるかに
より、正或いは負の電流を生成する。
り、それにより周波数を制御電圧により確定することも
できる。この電圧は、コンデンサに給電する電流生成源
により生成することもできる。制御装置は、それぞれ動
作周波数の増加或いは減少(発振器の設計によっては、
それぞれ減少或いは増加)のいずれが必要とされるかに
より、正或いは負の電流を生成する。
【0022】好適な発生器は、周波数源12、14の出
力14Aと発生器出力端子26との間に延在する、発生
器10の出力ライン24に接続される方向性結合器22
を介してUHF帯で電気外科用電力を供給する。図1に
示されるように、出力端子26は、使用中に患者30
に、詳細には治療されることになる組織に適用される治
療電極を有する電極アセンブリ28に接続される。
力14Aと発生器出力端子26との間に延在する、発生
器10の出力ライン24に接続される方向性結合器22
を介してUHF帯で電気外科用電力を供給する。図1に
示されるように、出力端子26は、使用中に患者30
に、詳細には治療されることになる組織に適用される治
療電極を有する電極アセンブリ28に接続される。
【0023】結合器22内においてサーキュレータを用
いて、全ての条件下で公称50Ω負荷を電力増幅器14
に与えることができる。最適化、利便性及びコストの点
から、個別の方向性結合器を用いることもできる。結合
器22は、無線周波数源12、14と電極アセンブリ2
8との間に直列に接続され、反射した電力は結合器の反
射電力出力22Bに配向され、その出力は、結合器22
に公称50Ωの反射電力ダンプを与える検出回路32に
接続される。
いて、全ての条件下で公称50Ω負荷を電力増幅器14
に与えることができる。最適化、利便性及びコストの点
から、個別の方向性結合器を用いることもできる。結合
器22は、無線周波数源12、14と電極アセンブリ2
8との間に直列に接続され、反射した電力は結合器の反
射電力出力22Bに配向され、その出力は、結合器22
に公称50Ωの反射電力ダンプを与える検出回路32に
接続される。
【0024】上記のように、完全な共役のインピーダン
スの整合が、発生器10と、電極アセンブリ28及びそ
の周辺物(患者30を含む)により示される電気的負荷
との間に存在しなければ、発生器の出力端子26から電
極アセンブリに供給される電力の一部が反射電力として
戻される。これは、制御システム20の入力20Aに対
する反射電力の大きさを示す反射電力出力信号を与える
検出回路32により電圧および/または電流として測定
される。
スの整合が、発生器10と、電極アセンブリ28及びそ
の周辺物(患者30を含む)により示される電気的負荷
との間に存在しなければ、発生器の出力端子26から電
極アセンブリに供給される電力の一部が反射電力として
戻される。これは、制御システム20の入力20Aに対
する反射電力の大きさを示す反射電力出力信号を与える
検出回路32により電圧および/または電流として測定
される。
【0025】制御システム20は、動作の最適な周波数
を確定するために、検出回路32からの反射電力出力信
号を使用する。電極が患者に適用される場合、発生器1
0が経験するインピーダンス状況は多くの部分が未知で
あり、それは最良の性能のために必要とされる発生器の
特性、特にその周波数が必ずしも予め知られているわけ
ではなく、使用中に変動することを意味することは理解
されよう。
を確定するために、検出回路32からの反射電力出力信
号を使用する。電極が患者に適用される場合、発生器1
0が経験するインピーダンス状況は多くの部分が未知で
あり、それは最良の性能のために必要とされる発生器の
特性、特にその周波数が必ずしも予め知られているわけ
ではなく、使用中に変動することを意味することは理解
されよう。
【0026】制御システムは、入力20Aの反射電力出
力信号をモニタしながら発振器12の周波数を変化させ
るように動作し、動作中の任意の所与の時間において最
適値に向けて周波数を移動させる。これを行うために、
反射電力出力信号は連続して、或いは定期的にモニタさ
れることができる。同様に、周波数源の周波数は連続し
て、或いは定期的に調整されることができる。
力信号をモニタしながら発振器12の周波数を変化させ
るように動作し、動作中の任意の所与の時間において最
適値に向けて周波数を移動させる。これを行うために、
反射電力出力信号は連続して、或いは定期的にモニタさ
れることができる。同様に、周波数源の周波数は連続し
て、或いは定期的に調整されることができる。
【0027】一形態では、周波数源の周波数は、その最
大範囲内で制御システムにより調整され、最大電力を送
給するための周波数が確定される。適当なデューティサ
ークルでこのプロセスを繰り返すことにより、最大電力
を送給することができる。このプロセスは、典型的には
5MHzの間隔だけ離れた異なる試験周波数で、例えば
20個の反射電力サンプルを得るために繰り返すことが
できる。これは、100MHzの試験帯域に帰結する。
20個のサンプルは典型的には、0.5秒毎に一度、2
ms内に取得される。他のユーザ及び近くの装置との干
渉を低減するために、電力制御出力20Bを介して、そ
の範囲に渡って周波数を調整するプロセス中に、電力出
力を一時的に低減することが好ましい。
大範囲内で制御システムにより調整され、最大電力を送
給するための周波数が確定される。適当なデューティサ
ークルでこのプロセスを繰り返すことにより、最大電力
を送給することができる。このプロセスは、典型的には
5MHzの間隔だけ離れた異なる試験周波数で、例えば
20個の反射電力サンプルを得るために繰り返すことが
できる。これは、100MHzの試験帯域に帰結する。
20個のサンプルは典型的には、0.5秒毎に一度、2
ms内に取得される。他のユーザ及び近くの装置との干
渉を低減するために、電力制御出力20Bを介して、そ
の範囲に渡って周波数を調整するプロセス中に、電力出
力を一時的に低減することが好ましい。
【0028】別の形態では、周波数源12、14の周波
数は、組織へより大きな電力を送給するために必要とさ
れる周波数調整の方向を判定するために、異なる周波数
間で切り替えられる。このプロセスは、さらなる改善が
得られないか、或いは電力送給が減少して周波数の変化
の方向を反対にするようになるまで、継続することがで
きる。最大電力送給のための周波数が固定された場合、
制御システムはその動作周波数を最適な周波数付近に切
り替えるようにする。
数は、組織へより大きな電力を送給するために必要とさ
れる周波数調整の方向を判定するために、異なる周波数
間で切り替えられる。このプロセスは、さらなる改善が
得られないか、或いは電力送給が減少して周波数の変化
の方向を反対にするようになるまで、継続することがで
きる。最大電力送給のための周波数が固定された場合、
制御システムはその動作周波数を最適な周波数付近に切
り替えるようにする。
【0029】別の形態では、所与の変調周波数及び変調
の深さにおける振幅変調が、制御システム20により、
或いは個別の変調器(図示せず)から無線周波数信号に
対して行われる。それゆえ無線周波数搬送波(動作の周
波数を有する)と、2つの側波帯(変調周波数に等しい
搬送波周波数の上下にオフセットした周波数を有する)
との間で変調の深さに応じて電力が分散される。2つの
側波帯は、等しい(或いは装置の電力出力が周波数とと
もに変動する場合に略等しい)量の電力を含む。反転電
力信号の測定により(検出回路32中の単側波帯検出器
を用いる)、2つの側波帯間のあらゆる著しい不均衡が
検出され、制御システム20が、動作周波数が調整され
るべき方向を判定できるようになる。
の深さにおける振幅変調が、制御システム20により、
或いは個別の変調器(図示せず)から無線周波数信号に
対して行われる。それゆえ無線周波数搬送波(動作の周
波数を有する)と、2つの側波帯(変調周波数に等しい
搬送波周波数の上下にオフセットした周波数を有する)
との間で変調の深さに応じて電力が分散される。2つの
側波帯は、等しい(或いは装置の電力出力が周波数とと
もに変動する場合に略等しい)量の電力を含む。反転電
力信号の測定により(検出回路32中の単側波帯検出器
を用いる)、2つの側波帯間のあらゆる著しい不均衡が
検出され、制御システム20が、動作周波数が調整され
るべき方向を判定できるようになる。
【0030】さらに別の実施形態では、周波数源12、
14は試験段階で動作し、試験段階中に、例えばスペク
トル拡散変調を用いて同時にいくつかの異なる周波数成
分を生成し、検出回路32が特定の周波数或いは比較的
狭帯域の周波数帯でサンプリングし、動作段階中の通常
動作に最も適した動作周波数を判定する。
14は試験段階で動作し、試験段階中に、例えばスペク
トル拡散変調を用いて同時にいくつかの異なる周波数成
分を生成し、検出回路32が特定の周波数或いは比較的
狭帯域の周波数帯でサンプリングし、動作段階中の通常
動作に最も適した動作周波数を判定する。
【0031】他の無線周波数ユーザ或いはその付近の装
置との無線周波数干渉を低減或いは防止するために、放
射された干渉波を低減するか、或いは特定の周波数或い
は周波数帯を使用しないようにするために、動作の周波
数を調整することができる。この例では、放射モニタ用
信号アンテナ36に応答して生成される検出回路32か
らの付加信号をモニタすることにより、制御システムは
周波数源12、14の周波数を変更するように構成され
る。このアンテナは患者の近く、典型的には数メートル
以内に配置され、検出回路32は、発生器10の動作帯
域内或いは他の帯域内(例えば動作周波数の高調波)の
信号を受信するように構成された受信機を含む。制御シ
ステム20は、入力20Aに加わる放射モニタ用信号を
モニタし、その信号がアンテナ36からの受信信号電力
を表しており、電力増幅器14の電力制御入力14Bを
介して、公称出力電力を低減するように処理される。
置との無線周波数干渉を低減或いは防止するために、放
射された干渉波を低減するか、或いは特定の周波数或い
は周波数帯を使用しないようにするために、動作の周波
数を調整することができる。この例では、放射モニタ用
信号アンテナ36に応答して生成される検出回路32か
らの付加信号をモニタすることにより、制御システムは
周波数源12、14の周波数を変更するように構成され
る。このアンテナは患者の近く、典型的には数メートル
以内に配置され、検出回路32は、発生器10の動作帯
域内或いは他の帯域内(例えば動作周波数の高調波)の
信号を受信するように構成された受信機を含む。制御シ
ステム20は、入力20Aに加わる放射モニタ用信号を
モニタし、その信号がアンテナ36からの受信信号電力
を表しており、電力増幅器14の電力制御入力14Bを
介して、公称出力電力を低減するように処理される。
【0032】同じ電力制御入力14Bを用いて、試験段
階、すなわち周波数源の周波数が、検出回路32を介し
て反射電力および/または放射電力をサンプリングする
ように変化させる試験段階中に、自動的に公称無線周波
数電力出力を低減することができる。
階、すなわち周波数源の周波数が、検出回路32を介し
て反射電力および/または放射電力をサンプリングする
ように変化させる試験段階中に、自動的に公称無線周波
数電力出力を低減することができる。
【0033】
【発明の効果】上記のように、この発明によれば、種々
の要因に起因する負荷インピーダンスの変化を考慮し
て、動作周波数を自動的に調整することにより性能が最
適化され、それにより電気外科システムの効率が改善さ
れる。
の要因に起因する負荷インピーダンスの変化を考慮し
て、動作周波数を自動的に調整することにより性能が最
適化され、それにより電気外科システムの効率が改善さ
れる。
【図1】 この発明による電気外科用信号発生器を含む
電気外科システムを示すブロック図である。
電気外科システムを示すブロック図である。
10 発生器、12 発振器(周波数生成源)、14
電力増幅器、14A出力、14B 電力制御入力、16
デジタル位相同期ループ、18 基準周波数源、20
制御システム、20A 入力、20B 電力制御出
力、22 結合器、22B 反射電力出力、24 出力
ライン、26 発生器出力端子、28電極アセンブリ、
30 患者、32 検出回路、34 入力端子、36
受信アンテナ。
電力増幅器、14A出力、14B 電力制御入力、16
デジタル位相同期ループ、18 基準周波数源、20
制御システム、20A 入力、20B 電力制御出
力、22 結合器、22B 反射電力出力、24 出力
ライン、26 発生器出力端子、28電極アセンブリ、
30 患者、32 検出回路、34 入力端子、36
受信アンテナ。
───────────────────────────────────────────────────── フロントページの続き (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 (18)
- 【請求項1】 無線周波数源と、反射電力検出回路と、
前記検出回路と前記周波数源とに接続される制御装置と
を備えた電気外科用信号発生器であって、前記制御装置
が、前記周波数源が異なる周波数源の周波数で動作する
とともに、反射電力を表す前記検出回路からの反射電力
出力信号を受信し、また相対的に低い反射電力レベルに
対応する値に前記周波数源の周波数を設定できるように
構成された電気外科用信号発生器。 - 【請求項2】 前記制御装置が、前記周波数源が定期的
に複数の異なる選択された試験信号を生成できるように
し、各試験周波数で前記出力信号をモニタし、その後、
概ね最小の反射電力に対応する動作周波数に前記周波数
源を設定するように構成された請求項1に記載の電気外
科用信号発生器。 - 【請求項3】 前記検出回路が、発生器電力出力ライン
に関連する電圧或いは電流モニタを備えた請求項1また
は2に記載の電気外科用信号発生器。 - 【請求項4】 前記モニタが前記出力ラインにハイブリ
ッド結合器を備えた請求項3に記載の電気外科用信号発
生器。 - 【請求項5】 前記制御装置が、前記発生器の動作中に
連続して前記検出回路からの前記出力信号をモニタし、
かつ前記出力信号が反射電力値の増加を示す閾値に到達
するのに応じて、設定周波数を調整するように構成され
た請求項1に記載の電気外科用信号発生器。 - 【請求項6】 前記制御装置が定期的に試験シーケンス
を実行するように構成され、前記シーケンスでは、前記
周波数源の周波数が所定の範囲に渡って変化し、前記出
力信号がモニタされ、その後治療段階において、最大送
給出力電力を示す前記出力に応じて選択された動作周波
数に前記周波数源を設定する請求項1に記載の電気外科
用信号発生器。 - 【請求項7】 前記制御装置が、少なくとも0.5秒毎
に前記試験シーケンスを実行するように構成された請求
項6に記載の電気外科用信号発生器。 - 【請求項8】 前記周波数源が、前記試験シークエンス
中、前記治療段階より低い電力設定で電気外科用電力を
送給するように構成された請求項6または7に記載の電
気外科用信号発生器。 - 【請求項9】 前記制御装置が、前記周波数源が周波数
源の異なる周波数間で切り替わるようにし、前記出力信
号をモニタして、前記送給される電気外科用電力を増加
するのに必要とされる周波数調整の方向を判定するよう
に構成された請求項1に記載の電気外科用信号発生器。 - 【請求項10】 前記制御装置が、前記切替え動作によ
り繰返し、かつ連続して最大電力に概ね対応する周波数
に前記周波数源の周波数を双方向的に調整できるように
構成された請求項9に記載の電気外科用信号発生器。 - 【請求項11】 前記周波数源に接続され、少なくとも
2つの異なる周波数成分を含むように前記周波数源出力
信号を変調するように構成された変調器と、前記検出回
路の一部を形成しかつ前記成分の周波数において反射さ
れた電力の大きさを示す反射電力出力信号を供給するよ
うに構成された検出器とを含む発生器であって、前記制
御装置が、前記異なる周波数成分に対応する反射電力の
相対的な大きさをモニタし、かつ前記送給された電気外
科用電力を増加させる方向に向かう値に前記周波数源の
周波数を調整するように構成された請求項1に記載の電
気外科用信号発生器。 - 【請求項12】 前記検出器が単側波帯検出器である請
求項11に記載の電気外科用信号発生器。 - 【請求項13】 前記制御装置および/または前記周波
数源が、試験段階中に、同時に複数の異なる周波数成分
を有する周波数源出力信号を生成するように構成され、
前記検出回路が、前記成分の周波数で反射電力信号をサ
ンプリングするように動作することができ、前記制御装
置が、動作周波数を選択するために、生成された前記セ
ンサ出力信号の値を処理するように構成された請求項1
に記載の電気外科用信号発生器。 - 【請求項14】 前記周波数成分がスペクトル拡散変調
により生成される請求項12に記載の電気外科用信号発
生器。 - 【請求項15】 放射モニタ用信号を受信するための入
力を備え、前記制御装置が、前記モニタ用信号を処理
し、かつ前記放射モニタ用信号の所定の特性に応じて前
記周波数源を調整する請求項1から14までのいずれか
に記載の電気外科用信号発生器。 - 【請求項16】 前記制御装置が、前記所定の特性に応
じて前記周波数源の前記動作周波数を調整するように構
成された請求項15に記載の電気外科用信号発生器。 - 【請求項17】 請求項1から16までのいずれかに記
載の電気外科用信号発生器と、前記電気外科用信号発生
器の出力に接続される少なくとも1つの治療電極を含む
電極アセンブリとを備えた電気外科システム。 - 【請求項18】 請求項15または16に記載の発生器
と、前記入力に接続されるアンテナとを備えた請求項1
7に記載の電気外科システム。
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
GB9912625.2 | 1999-05-28 | ||
GBGB9912625.2A GB9912625D0 (en) | 1999-05-28 | 1999-05-28 | An electrosurgical generator and system |
Publications (1)
Publication Number | Publication Date |
---|---|
JP2001008944A true JP2001008944A (ja) | 2001-01-16 |
Family
ID=10854471
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
JP2000158325A Withdrawn JP2001008944A (ja) | 1999-05-28 | 2000-05-29 | 電気外科用信号発生器及び電気外科システム |
Country Status (5)
Country | Link |
---|---|
EP (1) | EP1055399A1 (ja) |
JP (1) | JP2001008944A (ja) |
AU (1) | AU3645800A (ja) |
CA (1) | CA2308939A1 (ja) |
GB (1) | GB9912625D0 (ja) |
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Also Published As
Publication number | Publication date |
---|---|
CA2308939A1 (en) | 2000-11-28 |
EP1055399A1 (en) | 2000-11-29 |
GB9912625D0 (en) | 1999-07-28 |
AU3645800A (en) | 2000-11-30 |
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