JP3377887B2 - 電気外科用器具 - Google Patents

電気外科用器具

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Publication number
JP3377887B2
JP3377887B2 JP16245695A JP16245695A JP3377887B2 JP 3377887 B2 JP3377887 B2 JP 3377887B2 JP 16245695 A JP16245695 A JP 16245695A JP 16245695 A JP16245695 A JP 16245695A JP 3377887 B2 JP3377887 B2 JP 3377887B2
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Prior art keywords
generator
output
inductor
capacitor
electrode unit
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JPH0856955A (ja
Inventor
マーク ゴーブル ナイジェル
チャールズ オーウェン ゴーブル コリン
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Gyrus Medical Ltd
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Gyrus Medical Ltd
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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
    • 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
    • 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
    • A61B2018/0066—Sensing and controlling the application of energy without feedback, i.e. open loop control

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

Description

【発明の詳細な説明】
【０００１】
【産業上の利用分野】本願発明は、外科的処置中に及び
特に電気外科切断中に印加される無線周波数出力を増大
するための回路構成を含む電気外科用器具に関する。
【０００２】
【従来の技術】電気外科切断には、一般に、電気外科的
乾燥より高い出力電圧を必要とする。これに対する手段
を講じるため、電気外科用ジェネレータ内部に、乾燥に
用いるものと比較してより高い切断用の二次・対・一次
出力変圧器巻線比を有する出力変圧器を組込むことが知
られている。そのように巻線比が大きいため、特に所要
ピーク出力電流及び電力損失の点から、変圧器を駆動す
る出力装置に対する要求が増大することになる。この困
難事を克服するため、ジェネレータの出力インピーダン
スを、典型的には300Ωから500Ωまでの範囲の値まで、
増やすことが知られている。
【０００３】
【発明が解決しようとする課題】これは低値結合キャパ
シタを設けることにより達成してよいが、高負荷インピ
ーダンスで用いる時、電極の集合体とその電極集合体を
ジェネレータに結合する任意のケーブルの固有キャパシ
タンスによって結合キャパシタの両端での電圧降下を大
きくするという欠点がある。実際上、固有キャパシタン
スは、結合キャパシタとともに、負荷の両端にかかる電
圧を下げる分圧器を形成する容量性負荷インピーダンス
に相当する。電極集合体が湿ったところにある時は、有
効負荷キャパシタンスが高くなるので、問題はさらに厄
介なものとなる。この欠点を克服することが、本発明の
目的とするところである。
【０００４】
【課題を解決するための手段】本発明は、電気外科的電
極ユニットとその電極ユニットをジェネレータに結合す
る少なくとも１つのコンダクタ（導体、導線）を含む電
気負荷に結合される電気外科用ジェネレータから成り、
ジェネレータは結合コンダクタと直列にインライン出力
インダクタを有し、且つ負荷は容量性であり、負荷キャ
パシタンスと出力インダクタが連なってジェネレータの
動作周波数より高くしかも前記動作周波数の２倍より高
くない共振周波数を有する直列共振出力回路を形成する
ことを特徴とする電気外科用器具を提供する。
【０００５】負荷キャパシタンスは、もっぱらコンダク
タと電極ユニット及び隣合う導電性素子との間の固有キ
ャパシタンスから成ってよいが、少なくとも１つのキャ
パシタ、即ち、ジェネレータ出力の両端に結合されて、
固有キャパシタンスに追加される集中(lumped)キャパシ
タンスも包含することが望まれる。集中キャパシタンス
への追加又はその代替として、ジェネレータと電極ユニ
ットとを結合するコンダクタを包含する高キャパシタン
ス・ケーブルを用いてよい。
【０００６】本発明の一具体例では、電極ユニットは、
ケーブルによってジェネレータの出力端子に結合される
ハンドピース内に、取外しできるか又はできないように
して、収容される。ジェネレータ出力からの結合コンダ
クタはケーブルとハンドピースを介して電極ユニットの
電極まで延長する。この具体例では、ハンドピースは、
コンダクタ間に結合され従ってハンドピースが接続され
る時ジェネレータの出力端子間に結合されるところのキ
ャパシタを包含する。ハンドピースは別々の長さのケー
ブルを設けることができる故、任意の特定ハンドピース
のキャパシタ値は、少なくとも一部分、設けられるケー
ブル長に合うように選んでよい。従って、ケーブル中の
コンダクタの固有キャパシタンスはケーブル長によって
決まるので、キャパシタはハンドピースとケーブルの組
合せについて所望の全体又は総合キャパシタンスを生ず
るように選択してよい。ハンドピース内にキャパシタを
有することはまた、もし要すれば、所要の出力特性に応
じて、キャパシタを接続し及び断路するためのスイッチ
をキャパシタと直列にハンドピース内に設けることがで
きる、という利点ももたらす。事実、択一的なキャパシ
タ値がユーザによって選べるよう少なくとも２つのキャ
パシタを包含することが可能である。
【０００７】ジェネレータの出力端子間のキャパシタン
スとともにインラインインダクタを設けることにより、
及びもしジェネレータの動作周波数で生ずる直列共振回
路のＱが１より大なら、負荷両端の、事実上キャパシタ
ンス両端の使用電圧は、変圧器結合ジェネレータ出力段
の出力変圧器の二次巻線の巻線数を増やさなくても従来
技術で達成されるものより高い。すでに述べたように、
直列共振結合の共振周波数は、好ましくは、ジェネレー
タの動作周波数より高い。与えられた負荷インピーダン
スに対して望まれる範囲は、1.25ｆ〜2ｆであり、ここ
でｆは、そこで負荷への最大電力伝達が開放ループ条件
で（即ち、負荷インピーダンスの変動に応答して出力電
力の変動を引起こすフィードバック制御変調なしで）起
こるジェネレータの周波数である。そのジェネレータの
周波数で、直列共振結合のQは1.5から3までの範囲であ
ってよい。
【０００８】ジェネレータの動作周波数より高い共振周
波数では、直列共振結合は永久に同調から外れる。この
故意の不整合には２つの利点がある。先ず、電極ユニッ
トが湿った場所で使われる時、キャパシタンスが増えて
直列共振結合の共振周波数がより低くなり、結果的に共
振周波数がジェネレータの動作周波数により近づき、従
って負荷にかかる電圧が高められることになる。この方
法では、電極領域における電導性液体の影響は、さもな
ければそれ以上に達したであろう出力電圧の上昇によっ
て補償される。さらに、直列共振結合の同調は、それが
その共振ピーク・インピーダンスを外れて、即ち、特性
勾配が共振周波数により近いものより急峻でないそのイ
ンピーダンス対周波数特性上の諸点で用いられるので特
に重要ではない。
【０００９】ジェネレータの動作周波数は、その出力で
の負荷インピーダンスに応じて可変できてよい。典型的
には、動作周波数は、300kHzから500kHzまでの範囲内に
留まる。直列共振回路の動作周波数は、典型的には、45
0kHzと700kHzの間であり、乾燥条件での好ましい周波数
としては500kHz〜600kHzの範囲である。インライン・イ
ンダクタに対する代表値は、150μH〜250μHであり、好
ましい範囲は170μH〜210μHである。電極ユニット、及
び電極ユニットとジェネレータの出力端子の間の素子の
総合キャパシタンスは、350pFより大きくなるよう及び
好ましくは400pFより大きくなるよう配置されてよい。
【００１０】切断及び乾燥の両用として単一の出力を有
する電気外科用ジェネレータの場合、インライン・イン
ダクタが切換えられることが望まれ、その結果、切断が
必要なときはそれによってジェネレータの出力段を通し
て電力伝達経路部分が形成され、また、乾燥時のよう
に、低めの電圧出力が要るときはスイッチを切るか又は
バイパスされることになる。電極ユニットを登載してい
るハンドピースの内部にジェネレータを併合することは
可能であり、この場合、簡単なスイッチをハンドピース
のケーシング上に設けてよい。ジェネレータがケーブル
を介してハンドピースに接続される単独ユニットである
という最も一般的な状況では、スイッチは、ジェネレー
タのハウジング自体の上に設けてよく、又は、好ましく
は、インダクタの切換えは、ハンドピース上のスイッチ
から遠隔制御で実施してよい。事実、そのスイッチは、
ジェネレータをオンーオフ切換えする第二のスイッチと
同じ制御手段を使って操作してよい。このことは、１つ
以上の別のコンダクタをハンドピースとジェネレータ間
のケーブルに入れることにより行ってよく、ハンドピー
スは２つのスイッチ素子を含み、各々は、例えば、変圧
器結合リンクを介してジェネレータのリレーを動作させ
る。ハンドピースの両スイッチ素子を単一の制御ボタン
で動作させることは可能であり、その結果、外科医は、
先ずそのボタンを押して電気外科用電力を印加でき、そ
の後、もし要すれば、ジェネレータをオンするに必要な
押下げ以上にそのボタンをさらに押してインライン・イ
ンダクタの切換えにより切断用として出力電圧を上昇し
てよい。
【００１１】発明は、その第二の様相の通り、双極電極
ユニット；及び電極ユニットを登載しているハンドピー
スから成る電気外科用装置を包含しており、そのハンド
ピースは、電気外科用無線周波数電力をジェネレータか
ら電極ユニットの電極に伝達する一対の電力供給コンダ
クタと、電極ユニットと電力供給コンダクタの固有キャ
パシタンスを補足するためにコンダクタ間に接続された
キャパシタを包含する。
【００１２】
【実施例】発明の好ましい具体例を簡略した形で図１に
示す。電気外科用器具は、出力端子12A、12Bを有する出
力段10付きの無線周波数の電気外科用ジェネレータを有
している。ジェネレータは、少なくともそれが、出力変
圧器の二次巻線14と、二次巻線の両端に並列に結合され
た第一キャパシタ16と及び変圧器二次巻線とジェネレー
タの出力端子12A、12Bの１つとの間に直列に結合された
第二キャパシタ18とから成る共振出力回路を有する自己
同調出力発振器をもつ限りにおいて、好ましくは、英国
特許第2214430号 に開示された形状である。従って、共
振出力回路の共振周波数は、第二キャパシタ18によって
表される直列接続リアクタンス素子のためにジェネレー
タに生じたその端子12A、12B間の負荷インピーダンスに
よって一部分決定される。ジェネレータは、発振器にパ
ルスを発生させて出力電力を調整するための装置（未表
示）を有する。これはフィードバックループを用いて行
われる。本明細書において開放ループ条件に対する言及
は、そのフィードバックループが不能のジェネレータの
動作を意味するものである。
【００１３】器具はさらに電極20E を有する双極電極ユ
ニット20を包含しており、そのユニットは電力伝達コン
ダクタ22A、22Bによってジェネレータに結合されてい
て、各コンダクタは、ジェネレータのそれぞれの出力端
子12A、12Bの１つにそれぞれの電極を電気的に連接す
る。コンダクタ22A、22Bは、電極20E から電極ユニット
20を登載するハンドピース24を通して、及びハンドピー
スを接合するケーブル26を通してジェネレータまで通っ
ている。この好ましい具体例では、電極ユニットは、電
極ユニット20とハンドピース24の間で取り外しできる電
気接続を可能にする端子20A及び20Bを有していること、
及びハンドピース24は、ジェネレータ10の端子12A、12B
から、引き続いて取り外しできるケーブル26に永久的に
接続されていること、に気付くであろう。これは、ハン
ドピースとケーブルが、好ましくは単一体として供給さ
れる集合体を形成することを意味する。
【００１４】発明に従って、ジェネレータは、出力段変
圧器の二次巻線14とコンダクタ22A、22Bの１つとの間の
電力伝達経路の１つに直列素子を形成するインライン・
インダクタL を包含する。コンダクタ22A、22Bは、特に
それらが互いに密接して配置されるケーブル26において
固有の並列キャパシタンスを有することが分かるであろ
う。このキャパシタンスは、図１ではキャパシタンスCC
として示される。同様に、電極ユニットは、固有の並列
キャパシタンスCEを有し、これも図１に集中部品として
図式的に示されている。キャパシタンスCEは、電極20E
での状態に応じて変化する。湿った場所では、CEは、電
極20E の露出した電導面と接触している電導性流体に起
因して、ユニットが乾いている時よりかなり高くなる。
これらのキャパシタンスCCとCEに加えて、ハンドピース
24にはキャパシタCHがあり、このキャパシタンスは、予
め決めた値をもつキャパシタ部品である。全負荷キャパ
シタンスCC＋CH＋CEは、インライン・インダクタLと直
列共振回路を形成する。
【００１５】ジェネレータの動作周波数は、出力回路に
インダクタLを欠如した場合約340kHzと440kHzの間で変
化する。インダクタLの代表値は175μHである。キャパ
シタCHの値は、直列共振回路の共振周波数が約1.5ｆgen
になるよう選択され、ここでｆgenは、インダクタLが外
(out) に切換えられた開放ループで負荷への最大電力伝
達が生ずるジェネレータの動作周波数である。これは、
現在のケースでは、約100Ω の負荷抵抗に相当する。典
型的には、これは乾燥状態での全負荷キャパシタンスCC
＋CH＋CEに対して400pFと500pFの間の値を与える。実際
に、乾燥状態における電極ユニットは、約20pFのキャパ
シタンスをもち、キャパシタンスの残余はハンドピース
とケーブルの間で分割される。CHは、典型的には、150p
Fから350pFまでの範囲にある。
【００１６】キャパシタ18は、全負荷キャパシタンスCC
＋CH＋CEより約一桁大きい。従って、インダクタL と負
荷キャパシタンスによって形成される直列共振回路は、
ジェネレータ10の動作周波数に対してはその影響は比較
的小さい。
【００１７】ジェネレータがハンドピースに統合される
具体例では、コンダクタ22A、22Bの固有キャパシタンス
は、説明した具体例におけるよりもかなり小さくなるこ
とが分かるであろう。そのような場合、キャパシタCHは
相対的に大きくなる。
【００１８】バイパス・スイッチSは、インダクタLの両
端に接続され、それが実行されている電気手術の性質に
応じて随意に内(in)又は外(out)に切換えられる。図１
の具体例においてCHで表される付加キャパシタンスは、
ハンドピースに必ずしも編入される必要はない。特に、
それは、適当な長さを持ち且つ、例えば、メートル当り
100pFより大きいか、又は200pFをも越える高い固有キャ
パシタンスを有するケーブルを選択することにより編入
してよい。
【００１９】図１に示す配置では、負荷インピーダンス
が比較的高い時（例えば、１kΩ より上）、電極20E 両
端の出力電圧が上昇することになるが、図２に示すよう
にジェネレータの変圧器の二次巻線の巻数を増やしてさ
らに改善することもできる。ここでは、二次巻線は２つ
の部分14A、14Bになり、キャパシタ16は、二次巻線の大
きい方の主要部分14Aの両端にだけ結合される。この具
体例では、部分14Aは部分14Bのそれの２倍の巻数をも
つ。インライン・インダクタLは、ジェネレータ出力段
（特に二次巻線の部分14B ）と出力端子12A、12Bの１つ
との間に直列に結合される。この場合は、ジェネレータ
の自己同調発振器の周波数に影響するところの、共振回
路の第二キャパシタ18は、インライン・インダクタLと
出力端子12Aとの間に接続される。インライン・インダ
クタが回路に入る時、キャパシタ18とインダクタLの接
続順序は重要でないことが分かるであろう。ケーブル、
ハンドピース、及び電極ユニットは、図１のキャパシタ
CC、CH、及びCEで構成される単一の負荷キャパシタンス
CLとともに簡略した形で示されている。
【００２０】この具体例では、インライン・インダクタ
Lは、付加的二次巻線と共に、切換えスイッチ素子SCに
よって入力回路に入(in)及び出(out)に切換えられ、そ
の結果、乾燥に対しては、出力端子12A、12Bは二次巻線
の主部14A の両端にだけ結合される。より高い出力電圧
が必要な時、例えば、電気外科切断に対しては、スイッ
チ素子SCは、むしろ、直列即ちインラインインダクタL
と組合わせて二次巻線の両方の部分14A、14Bの両端にジ
ェネレータ出力端子を接続するよう操作される。前述の
ように、直列共振回路は、インライン・インダクタL と
負荷キャパシタンスCLによって形成され、共振周波数
は、その動作周波数範囲の全てでないとしても大部分に
わたり、ジェネレータの動作周波数より高い。
【００２１】スイッチ素子SCは、好ましくは、切換えリ
レーの接極子と接点である。便宜上、このリレーはハン
ドピース上の押ボタンスイッチ（未表示）によって遠隔
操作してよく、このスイッチは、動作時、ケーブル中の
電線32とコネクタ12C を通してジェネレータ10の動作コ
イル34に接続されているスイッチ30を閉じるものであ
る。ジェネレータの出力をオン・オフするために、同じ
押ボタンスイッチを用いて、別の電線38と別のコネクタ
12D によってジェネレータの別のコイル40に接続された
ハンドピースの別のスイッチ36を動作させてよい。
【００２２】図２の回路におけるインライン・インダク
タL の切換えの効果を図３に示す。この図は負荷へ伝達
される出力電力を負荷インピーダンスの関数としてプロ
ットしたグラフであり、ジェネレータの出力は、パルス
幅変調され、その電力をこの場合は約20ワットに制限す
る。点線の曲線は、インライン・インダクタL が外 (ou
t) に切換えられた場合の電力／インピーダンス特性を
示す。この設定は乾燥に用いられよう。実線の曲線は、
インライン・インダクタL の切換えの効果を示すもので
ある。比較的高い負荷インピーダンスでの電力出力は、
事実上増加し、且つ、加えて、対数目盛上では、電力カ
ーブの幅が大きくなることが注目されよう。両曲線は、
ほぼ平坦な中央部を持っている。これらの部分では、出
力電力は、発振器にパルスを発生させることにより限定
される。
【００２３】
【発明の効果】本発明により前記課題を解決することが
できる。
【図面の簡単な説明】
【図１】発明による電気外科用器具の簡略回路図；
【図２】発明による代替器具部分の回路図；
【図３】負荷インピーダンスに関する出力電力の変化を
示すグラフ図。
【符号の説明】
10…出力段 10…ジェネレ
ータ 12A、12B…出力端子 14…出力変圧
器の二次巻線 14A,14B…二次巻線の２つの部分 16…第一キャ
パシタ 18…第二キャパシタ 20…双極電極
ユニット 20A,20B…端子12C…コネクタ 12D…コネクタ 20E…電極 22A、22B…電力伝達コンダクタ 24…ハンドピ
ース 26…ケーブル 30…スイッチ 32…電線 34…動作コイ
ル 36…スイッチ 38…電線 40…コイル CC…キャパシ
タンス CE…並列キャパシタンス CH…キャパシ
タ L…インダクタ S…バイパス
・スイッチ CL…単一の負荷キャパシタンス SC…スイッチ
素子
───────────────────────────────────────────────────── 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，ウェールズ，ＣＦ64 １Ａ Ｔ，サウス グラモーガン，ペナーズ, クライブ クレセント，オズボーン ハ ウス ５番地 (56)参考文献 特開 昭54−98075（ＪＰ，Ａ) 特開 平５−200046（ＪＰ，Ａ) 特開 昭50−74754（ＪＰ，Ａ) 特開 昭58−41543（ＪＰ，Ａ) 特公 昭63−21504（ＪＰ，Ｂ２) 特公 平５−85177（ＪＰ，Ｂ２) (58)調査した分野(Int.Cl.7，ＤＢ名) A61B 18/12

Claims (14)

    (57)【特許請求の範囲】
  1. 【請求項１】 電気外科用電極ユニット(20)とジェネレ
    ータにその電極ユニット(20)を結合する少なくとも１つ
    のコンダクタ(22A) とを含む電気的負荷に連結され、ジ
    ェネレータ出力部を有する電気外科用ジェネレータから
    成り、ジェネレータが結合コンダクタ(22A) と直列にイ
    ンライン出力インダクタ(L) を有することと、負荷が容
    量性であり、負荷のキャパシタンス(CC、CH、CE；CL)と
    出力インダクタ(L) が連なってジェネレータの動作周波
    数より高くしかも前記動作周波数の２倍より高くない共
    振周波数を有する直列共振出力回路を形成することを特
    徴とする電気外科用器具。
  2. 【請求項２】 電気的負荷が、ジェネレータ出力の両端
    に結合される集中キャパシタンスを形成する少なくとも
    1つのキャパシタ(CH) を包含することを特徴とする請求
    項１記載の器具。
  3. 【請求項３】 電極ユニット(20)がハンドピース(24)に
    収容されており且つキャパシタ(CH)がハンドピース(24)
    に設けられていることを特徴とする請求項２記載の器
    具。
  4. 【請求項４】 電極ユニット(20) が一対の電極(20E)を
    有する双極ユニットであって、その各電極がハンドピー
    ス(24)を通過するそれぞれのコンダクタ(22A、22B)によ
    ってジェネレータのそれぞれの出力端子(12A、12B)に接
    続されることと、キャパシタ(CH)がコンダクタ(22A、22
    B) の間に接続されることとを特徴とする請求項３記載
    の器具。
  5. 【請求項５】 キャパシタ(CH)の接続及び遮断のために
    スイッチが用いられることを特徴とする請求項３又は４
    記載の器具。
  6. 【請求項６】 前記スイッチがハンドピース(24)のとこ
    ろに設けられた請求項５記載の器具。
  7. 【請求項７】 前記共振周波数がＫｆに等しく、ここで
    Ｋは1.25から2までの範囲であり、ｆは負荷への最大電
    力伝達が開放ループ条件で生ずるジェネレータの周波数
    であることを特徴とする請求項１から６の何れかに記載
    の器具。
  8. 【請求項８】 直列共振回路のQが1.5から3までの範囲
    である請求項１から７の何れかに記載の器具。
  9. 【請求項９】 ジェネレータの動作周波数が300kHzから
    500kHz までの範囲であり、インダクタ(L)が150μHから
    250μHまでの範囲の値を有する前記請求項１から８の何
    れかに記載の器具。
  10. 【請求項１０】 ジェネレータが切断及び乾燥用の単一
    出力と、スイッチ(S；Sc)が切断モード状態にある時イ
    ンダクタ(L)が負荷への電力伝達経路の一部を形成し且
    つスイッチ(S；Sc)が乾燥モード状態にある時インダク
    タ(L)がバイパスされるよう接続されるスイッチ(S；Sc)
    とを有することを特徴とする請求項１から９の何れかに
    記載の器具。
  11. 【請求項１１】 並列共振回路(14、16；14A、16)、結
    合コンダクタ(22A)によって電極ユニット(20) へ接続す
    るための出力端子(12A)、及びその端子に接続された時
    容量性負荷のキャパシタンス(CC、CH、CE；CL)と共にジ
    ェネレータの動作周波数より高く前記動作周波数の２倍
    より高くない共振周波数を有する直列共振回路を形成す
    るために共振出力回路と端子間に直列に接続されたイン
    ダクタ(L)とを有する出力段(10)から構成される電気外
    科用ジェネレータ。
  12. 【請求項１２】 前記ジェネレータが300kHzから500kHz
    までの範囲の周波数で操作可能であり、且つインダクタ
    (L) の値が150μHから250μHまでの範囲にあることを特
    徴とする請求項11記載のジェネレータ。
  13. 【請求項１３】 前記ジェネレータが乾燥と切断モード
    間を切換えるためのモード制御を包含し、前記モード制
    御には、乾燥モードにおいてインダクタ(L) がバイパス
    され、且つ切断モードでインダクタが共振出力回路(10)
    と端子(12A) 間に直列に接合されるよう接続されるスイ
    ッチ(S；Sc) が包含されることを特徴とする請求項11又
    は12記載のジェネレータ。
  14. 【請求項１４】 各供給コンダクタ(22A、22B)によりジ
    ェネレータ出力部へ接続された複数の電極(20E)を含ん
    だ双極電極ユニット(20)を含む電気的負荷に連結された
    ジェネレータ出力部を有する電気外科用ジェネレータか
    ら成る電気外科用装置であって、 前記ジェネレータは、並列共振回路(14、16)と、供給コ
    ンダクタ(22A、22B)の一つに直列に接続されたインライ
    ン出力インダクタ（L）とを含んだ共振出力回路を含
    み、 前記供給コンダクタ(22A、22B)と双極電極ユニット(20)
    とを含む前記電気的負荷はジェネレータ出力部へのキャ
    パシタンス(CC、CH、CE；CL)を形成し、前記キャパシタ
    ンス(CC、CH、CE；CL)は共振周波数がジェネレータの動
    作周波数より高いが前記動作周波数の２倍より高くない
    直列共振回路を形成することを特徴とする電気外科用装
    置。
JP16245695A 1994-06-29 1995-06-28 電気外科用器具 Expired - Fee Related JP3377887B2 (ja)

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GB9413070:5 1994-06-29
GB9413070A GB9413070D0 (en) 1994-06-29 1994-06-29 Electrosurgical apparatus

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JPH0856955A JPH0856955A (ja) 1996-03-05
JP3377887B2 true JP3377887B2 (ja) 2003-02-17

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EP (3) EP0694290B1 (ja)
JP (1) JP3377887B2 (ja)
AU (1) AU710629B2 (ja)
DE (2) DE69519405T2 (ja)
GB (1) GB9413070D0 (ja)

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DE69519405D1 (de) 2000-12-21
AU2324195A (en) 1996-01-11
AU710629B2 (en) 1999-09-23
EP0694290A2 (en) 1996-01-31
DE69534881T2 (de) 2006-09-07
EP1693015A3 (en) 2009-08-05
EP1034746B1 (en) 2006-03-22
JPH0856955A (ja) 1996-03-05
EP1693015B1 (en) 2012-02-29
US5647869A (en) 1997-07-15
EP1034746A3 (en) 2000-10-18
EP0694290A3 (ja) 1996-03-13
DE69534881D1 (de) 2006-05-11
EP1693015A2 (en) 2006-08-23
EP1034746A2 (en) 2000-09-13

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