JP2002528039A

JP2002528039A - Heat ablation system and method for tissue using porous electrode structure

Info

Publication number: JP2002528039A
Application number: JP53838397A
Authority: JP
Inventors: スワンソン，デイビッド・ケイ; パネスク，ドーリン; フェイン，ジェイムズ・ジー; オーウェンズ，パトリック・エム; フレイシュマン，シドニー・ディ; トンプソン，ラッセル・ビー; ジャクソン，ジェローム
Original assignee: BOSTON SCIENTIFIC LIMITED
Current assignee: BOSTON SCIENTIFIC LIMITED
Priority date: 1996-01-19
Filing date: 1997-01-17
Publication date: 2002-08-27
Anticipated expiration: 2017-01-17
Also published as: JP4361136B2

Abstract

(57)【要約】実質的に液体の灌流なしに電気エネルギーのイオン輸送を可能にする組織の加熱切除システム及び方法のための多孔質電極アセンブリー。 (57) [Summary] A porous electrode assembly for a tissue ablation system and method that enables ion transport of electrical energy without substantially liquid perfusion.

Description

【発明の詳細な説明】関連出願この出願は、それ自体が『心臓のマッピング及び切除システム』の名称で１９９２年９月２５日に出願された審査中の米国特許出願番号第０７／９５１，７２８号の一部係属出願である『心臓に導入中に扁平状態になる大きな表面を有した心臓切除カテーテル』の名称で１９９３年７月３０日に出願された審査中の米国特許出願番号第０８／０９９，９９４号の一部係属出願である。発明の分野本発明は、一般に身体の内部で展開される電極構造に関する。より具体的には、本発明は、心臓病の状態を診断したり治療するために心臓内に展開可能な電極構造に関する。発明の背景心臓の不整脈の治療には、治療される不整脈の特定の生理機能に基づいて、多様で異なった幾何図形的外形や特徴を有した組織損傷を創り出すことができる電極が必要とされる。例えは、従来からの８Ｆ型の直径／４ｍｍの長い心臓切除電極は、約０．５ｃｍの深さと約１０ｍｍの幅を有し且つ０．２ｃｍ³にも及ぶ損傷容積を有した損傷を心筋組織に創り出すために無線周波数エネルギーを伝達できるものである。これらの小さくて浅い損傷は、洞結節改造を行う為に洞結節に必要とされたり、又は色々な付属的な行路切開の為のＡ−Ｖ溝に沿って、又は心房痙攣（ＡＦＬ）の為の又はＡＶ結節スローパスウェイ切開の為の三尖弁峡のスローゾーンに沿って必要とされるものである。しかし、消化器官の頻脈（ＶＴ）の基質を除去するには、１．５ｃｍより深い浸透深さで、２．０ｃｍより大きい幅で、少なくとも１ｃｍ³の損傷容積を有した大幅により大きく且つより深い損傷を必要とするものと思われる。更に、浅い深度で比較的大きな表面積を有した損傷を創り出す必要性も残っている。多様な損傷特徴を創り出すために提案された一つの解決策は、異なった形の切除エネルギーを使うことである。しかし、マイクロウェーブやレーザや超音波による切除や化学的切除をとりまく周辺技術については、大方この目的に対して試験されていない。ＤＣや無線周波数の切除エネルギーの伝達に関連して積極的に冷却する方法を採用することは、電極と組織の中間面を強制的により低い温度とするものであることは知られている。結果的に、最も高温の組織温度領域が組織内によりフトされ、それで次には、切除によって生きられなくなった組織の境界を組織内により深くシフトさせることになる。積極的に冷却される電極は、積極的に冷却されていない同じ電極と比較してより多くの切除エネルギーを組織内に伝達するために使用される。しかし、組織の脱水や組織の煮沸が起きることが知られている約１００℃よりも低く安全に最高の組織温度を保つように積極的冷却の制御が必要とされる。表面積及び／若しくは深さのいずれにおいてもより大きな損傷を創り出すために提案されたもう一つ別の解決策は、市場で入手できるものよりも実質的により大きな電極を使用することである。然し、より大きな電極自身、寸法上及び操作性で幾つかの問題を有しており、重くなって静脈や動脈を通して大きな電極を心臓内に安全且つ容易に導入するのを妨害することになる。異なった幾何図形的外形と特徴を有した損傷を選択的に創り出すことができる多目的心臓切除電極に対するニーズがある。多目的電極は、安全且つ容易に心臓内に導入できるようにする上で必要な可撓性と操作性を有するであろう。一旦心臓の内側で展開されると、これらの電極は、制御された状態で、大きくて深い損傷でも、小さくて浅い損傷でも、大きくて浅い損傷でも必要とされる治療に応じて創り出すに足るエネルギーを発射する能力を有している。発明の大要本発明は、実質的に液体を散布しなくても電気エネルギーのイオン輸送を起こすことができるもので、組織の加熱切除システムに使用される各種の多孔質電極組立体（アセンブリー）を提供する。本発明の特長を具体化する多孔電極組立体は、外側が内側領域を周囲に渡って取り囲んでいる壁を有している。管腔（ルーメン）がイオンを含んだ媒体を内側領域内に搬送する。一つのエレメントが、内側領域内の媒体を電気エネルギー源に結合している。本発明の一局面に依れば、壁の少なくとも一部分は、媒体中に含まれているイオンの通過を許容しつつも巨大分子の通過を阻止する寸法の多孔質素材から構成されている。それによって、壁は、多孔質素材を通して壁の外部への電気エネルギーのイオン輸送を行えるようにしている。本発明のもう一つ別の局面に依れば、壁の少なくとも一部分は、多孔質素材中に実質的に液体散布をしなくても媒体中に含まれたイオンを通過させる寸法の多孔質素材から構成されている。それによって、壁は、壁中に実質的に液体を散布すること無しに多孔質素材を通して壁の外部へ電気エネルギーのイオン輸送をできるようにしている。本発明のもう一つ別の局面に依れば、壁の少なくとも一部分は、媒体中に含まれたイオンを通す寸法の多孔質素材から構成されており、それによって多孔質素材を通して壁の外部へ電気エネルギーのイオン輸送をできるようにしている。本発明のこの局面に依れば、多孔質素材は、内部圧力よりも大きな泡立ち点の値を有している。本発明のもう一つ別の局面に依れば、壁の少なくとも一部分は、媒体中に含まれたイオンを通す寸法の親水性の多孔質素材から構成されており、それによって多孔質素材を通して壁の外部へ電気エネルギーのイオン輸送をできるようにしている。本発明のこの局面に依れば、多孔質素材は、内部圧力よりも大きな泡立ち点の値を有しており、それによって多孔質素材中に実質的に液体散布を行わなくてもイオン輸送が起きる。本発明の他の特長及び長所は、次の説明と図面において述べられている。図面の簡単な説明図１は、本発明の特長を具体化する拡張可能な多孔質電極構造体を有した心臓組織切除システムの平面図である。図２は、電極構造体をその拡張された形態で示している、図１に示されたシステムに関連して使用される多孔質電極構造体の部分破断の拡大側部立面図である。図３は、電極構造体をその萎んだ形態で示している、図２に示された多孔電極構造の拡大側部立面図である。図４は、図２に示された多孔質電極構造体の部分的に破断し且つ更に拡大した幾分図表式な側面図である。図５は、内部の細長撓み材支持構造体の存在に依って電極構造体をその拡張された形態で示している、図１に示されたシステムに関連して使用される多孔質電極構造体の部分破断の拡大側部立面図である。図６は、外部摺動シースの操作によって電極構造体をその萎んだ形態で示している、図５に示された多孔質電極構造体の拡大側部断面図である。図７は、内部の織合せメッシュの支持構造体の存在に依って電極構造体をその拡張された形態で示している、図１に示されたシステムに関連して使用される多孔質電極構造体の部分破断の拡大側部立面図である。図８は、図４に示された電極本体の細孔を横切ってイオン電流密度を示している、図４の線８−８にほぼ沿って取り出され拡大された幾分図表式の拡大図である。図９は、検出されたインピーダンスと図４に示された電極本体の細孔を通るイオン輸送との間の関係を示したグラフである。図１０は、多孔発泡体から構成された電極構造体をその拡大された形態で示している、図１に示されたシステムに関連して使用される代替の多孔質電極構造体の部分破断の拡大側部立面図である。図１１は、その構造体の細孔を本体の末端部において雄牛の目のパターンに配列している、図１に示されたシステムに関連して使用される多孔質電極構造体の拡大側面図である。図１２は、その構造体の細孔を本体の側面に沿って周囲方向に隔設された区画状態で配列した、図１に示されたシステムに関連して使用される多孔質電極構造体の拡大側面図である。図１３は、図１２に示された区画状態の細孔領域に液体を搬送する多数の部屋を使用しているのを示している部分破断の側面図である。図１４は、更に無孔電極エレメントも保持している、図１に示されたシステムに関連して使用される多孔質電極構造体の拡大側部立面図である。図１５は、構造本体を蛇行して通ったワイヤによって形成された電極エレメントも保持している多孔質電極構造体の拡大側部断面図である。図１６は、内部のペース配分／検出用電極を備えた多孔質電極構造体の拡大側部立面図である。図１７と１８は、異なった条件で操作された時の多孔質電極構造体に関連した組織温度プロフィールを図表的に表示している。図１９は、多孔質素材の平坦シートから多孔質電極本体の末端部に半球形状を形成するための据付け物とマンドレルを幾分図式的に示した図である。図２０は、多孔質素材の平坦シートで半球状末端部外形を形成する工程における図１９に示された据付け物とマンドレルの側部断面図である。図２１は、半球状末端部外形の成形後の多孔質素材シートの拡大側部断面図である。図２２は、図２１に示された予じめ成形されたシートから多孔質電極本体の近位端部の半球形状を形成するための仕上げ据付け物を幾分図式的に示した図である。図２３は、図１９から２２に示された装置によって形成された後の多孔質電極本体の立面図である。図２４は、図２１に示された予じめ成形されたシートから多孔質電極本体の近位端部の半球形状を形成するために、図２２に示された仕上げ据付け物に代えて使用される拡張可能な仕上げ据付け物を幾分図式的に示した図である。図２５は、図２４に示された拡張可能な据付け物によって形成された後の多孔質電極本体の立面図である。図２６は、複合形の多孔質電極本体に共に結合される前の多孔質電極本体の２つの予じめ成形された半球状本体部分を幾分図式的に示した図である。図２７は、図２６に示された２つの半球状部分を周囲シームに沿って結合することによって形成された複合形多孔質電極本体の側部立面図である。図２８Ａは、直接組織に接触させないように本体の内側に周囲シームを設けるために、図２７に示された多孔質電極本体を裏返しにしているのを示した側部断面図である。図２８Ｂは、周囲シームを本体の内側に設けるために裏返しにされた後の図２７に示された多孔質電極本体の側部断面図である。図２９Ａは、２つの半球状部分を軸方向シームに沿って結合し、軸方向シームを本体の内側に設けるために裏返した後に形成された多孔質電極本体の側部断面図である。図２９Ｂは、図２９Ａに示された裏返された軸方向シームを有した多孔質電極本体の頂面図である。図３０は、主軸方向シームに沿って２つの半球状部分を結合し、付加の中間軸方向シームで本体を区画し、裏返した後にそれら軸方向シームを本体の内側に設けて形成された多孔質電極本体の頂面図である。図３１Ａは、多孔質素材の２枚のシートを共に結合して電極本体を形成するもので、温度検出エレメントをそのシーム内に包囲した本体を裏返す以前のシームの拡大側部断面図である。図３１Ｂは、温度検出エレメントをそのシーム内に包囲した本体を裏返す以前の、図３１Ａに部分的に示されたシーム結合本体の側部立面図である。図３１Ｃは、裏返し後にシームと温度検出エレメントの信号ワイヤとを本体内側に設けている、図３１Ｂに示された本体の側部断面図である。図３２Ａは、拡張可能な据付け物を使用して浸漬によって再生セルロース材から形成されている多孔質電極本体を幾分図式的に示した図である。図３２Ｂは、拡張可能な据付け物を取外して操縦組立体を備えた据付け物を本体の末端に取付けた後で、また裏返しする前の、図３２Ａで形成されている浸漬成形本体を示している。図３２Ｃは、裏返し後の、図３２Ｂに示された末端据付け物と操縦組立体とを備えた浸漬成形本体を示している。図３３は、半径を長さに沿って変えて末端領域と近位端の首領域を形成して細長い円筒外形状に成形された例示的な多孔本体を示している。図３４Ａは、長さに沿って一定の半径の細長い円筒外形のチューブとして成形されたもう一つ別の例示的な多孔本体を示している。図３４Ｂ、末端をシームによって閉鎖し、カテーテルチューブに取付けるためのボートチューブを近位端にシールしている、図３４Ａに示されたチューブを示している。本発明は、その精神又は必須の特徴から逸脱しない限り幾つかの形に具現されるものである。本発明の技術的範囲は、請求の範囲の前に記載されている具体的説明よりはむしろそれら添付の請求の範囲において定義されている。従って、請求の範囲の趣意及び同等範囲内に入る全ての実施例は、請求の範囲によって包含されるものである。好適な実施例の説明図１は、本発明の特長を具体化する組織切除システム１０を示している。本システム１０は、近位端１４と末端１６とを有した可撓カテーテルチューブ１２を有している。近位端１４は、ハンドル１８を備えている。末端１６は、本発明の特長を具体化する電極構造体２０を備えている。電極構造体２０の目的は、切除エネルギーを伝達するものである。図２と３に最も良く示されているように、電極構造体２０は、拡張可能で−萎むことができる本体２２を有している。本体２２の外形は、萎んだ形態（図３）と拡大された又は拡張された形態（図２）との間で変えられる。図示された好適な実施例では、拡張可能で−萎むことができる本体２２を膨らませて拡張された形態に維持するために液体圧力が使用される。この構成（図２を見よ）では、カテーテルチューブ１２は、その長さに沿って内部管腔３４を有している。管腔３４の末端は、拡張可能で−萎むことができる本体２２の中空な内部に開放している。内部管腔３４の近位端は、ハンドル１８のポート３６（図１を見よ）と連通している。液体の膨張用媒体（図２の矢印３８）は、ポート３６を通して管腔３４内に正圧下で搬入される。液体媒体３８は、拡張可能で−萎むことができる本体２２の内部を満たす。液体媒体３８は、内部圧力を働かせて拡張可能で−萎むことができる本体２２をその萎んだ形態からこの特徴によって、拡張可能で−萎むことができる本体２２が静脈構造内に導入されると、萎んだ低い形状（理想的には８フランス直径より小さい、即ち約０．２６７ｃｍより小さい）を取ることができるようになる。一旦所望の位置に配置されると、拡張可能で−萎むことができる本体２２は、例えば約７〜２０ｍｍの十分に拡張した形態に変換される。図５から７が示すように、構造体２０は、必要ならば、本体２２を拡張形態に維持するために液体媒体圧力を増大させたり又は取って代わる内部力を加える通常開放していて萎むことができる内部支持構造体５４を備えることができる。内部支持体５４の形状は変えられる。それは、例えば図５に示されているようにな可撓な細長いエレメント２４の組立体や、図７に示されているような内部の多孔な織成メッシュや開放型多孔発泡構造体２６からも構成される。これらの構成（図６を見よ）では、内側から支持された拡張可能で−萎むことができる本体２２は、カテーテルチューブ１２に沿って摺動する外部シース２８（図６を見よ）によって加えられる外部圧縮力によって膨張用媒体の除去後に萎んだ形態に変換される。図６に示すように、シース２８の前方移動によってそれを拡張可能で−萎むことができる本体２２を覆うように前進させる。拡張可能で −萎むことができる本体２２は、シース２８内部でその低い形状形態に萎む。シース２８の後方移動（図５又は７を見よ）によってそれを拡張可能で−萎むことができる本体２２から離れるように引き込ます。シース４８による拘束から解放されると、内部支持構造体５４は、スプリング力で開き、拡張可能で−萎むことができる本体２２をその拡張した形態に戻し、液体媒体を受け入れる。図４が最も良く示しているように、構造体２０は、更に導電材製の内部電極３０を本体２２の内部に設けている。内部電極３０の素材は、相対的に高い導電率と比較的高い熱伝導率の両方を有している。これらの特徴を備えた素材には、金、プラチナ、プラチナ／イリジウム等がある。貴金属が好ましい。絶縁された信号ワイヤ３２が、電極３０に接続されている。信号ワイヤ３２は、電極３０からカテーテルチューブを通ってハンドル１８（図１を見よ）上の外部コネクター３８へ延びている。コネクター３８は、電極３０を無線周波数発生器４０に電気的に接続している。好適な図示の実施例（図１を見よ）では、制御器４２に統合されたユニットとして又は独立した整合箱として、それらのいかずれかで無線周波数発生器４０に組み合わされている。制御器４２は、予じめ確立された基準に従って電極３０への無線周波数エネルギーの供給を制御する。更に、本システム１０のこの局面の詳細については、後述する。本発明に依れば、本体２２を満たす為に使用される液体媒体３８は、導電性液体である。液体３８は、電極３０から無線周波数エネルギーを運ぶ導電経路を形成する。関連して、本体２２は、少なくともその表面の一部分に細孔４４を有している非導電性熱可塑性材又は弾性材から構成されている。多孔本体２２の細孔４４（図解目的のために図４に図表的に拡大形状で示されている）は、電極３０からの切除エネルギーを導電性媒体３８を介して本体外側の組織にイオン輸送させる。好ましくは、液体３８は、本体２２内におけるオーム損失を、かくしてオームの加熱作用を低減する小さい抵抗を有している。図示の好適な実施例では、液体３８は、更に少なくとも部分的に本体の膨張用媒体としての付加的作用も行う。導電性液体３８の成分は変えられる。図示の好適な実施例では、液体３８は、容積当り約９重量％の飽和の又は近飽和の塩化ナトリウム濃度を有した高浸透圧の塩水から構成されている。高浸透圧の塩水は、約１５０Ω・ｃｍの血液抵抗や約５００Ω・ｃｍの心筋組織抵抗と比較してほんの約５Ω・ｃｍだけ低い抵抗となっている。導電性液体３８の成分は、高浸透圧の塩化カリウム溶液から構成されている。この媒体は、所望のイオン輸送を促進するが、カリウム過負荷を防ぐために、イオン輸送が細孔４４を通過する速度をより精密に監視する必要がある。高浸透圧の塩化カリウム溶液が使用された場合、イオン輸送速度を約１０ｍＥｑ／分未満に保つことが望ましい。ちょうど説明してきたように、本システム１０は、心臓内の心筋組織の切除に理想的に適している。この実施例では、外科医が大静脈又は動脈を通して心室内までカテーテルチューブ１２を移動させるが、その間は電極構造体２０の拡張可能で−萎むことができる本体２２は、その低形状形態になっている。一旦所望の心室内において拡張可能で−萎むことができる本体２２がその拡張した形態に拡張されると、細孔４４を有した領域は、心臓内組織の目標領域と接触するように拡張される。大方、細孔４４に渡る質量濃度差に依って、媒体３８内のイオンは、濃度差によって起こされる拡散のために細孔４４内を通って行くことになる。細孔４４を通る拡散は、濃度勾配が本体２２に渡って維持されている限り持続する。細孔４４に含まれたイオンは、本体２２を横切って電流を導く手段を提供している。無線周波数エネルギーは、制御器４２によって制御されて発生器４０から電極３０に搬送される。無線周波数（ＲＦ）電圧が電極３０に印加されると、電流は細孔４４内のイオンによって運ばれる。イオンはＲＦ周波数を加えている間に若干前後に移動するが、もしＤＣ電圧が印加されると生じるように、イオンによって提供されるＲＦ電流は、何らイオンの正味の拡散を起こさない。加えられたＲＦ場に応答したこのイオン運動（及び電流の流れ）は、細孔４４を通した媒体３８の液体散布を必要としない。イオンは、無線周波数エネルギーを細孔４４を通して戻り電極に対面した組織内へ運ぶが、戻り電極は、一般に（単極構造を形成する）外部パッチ電極となっている。代わりに、伝達されたエネルギーは、組織を通って（双極構造を形成する）心室内の隣接電極に通ることができる。無線周波数エネルギーは、大部分電気抵抗的に組織を加熱して治療用損傷を形成する。本体２２の電気抵抗は、損傷の形状と制御性に大きな影響を有している。低い抵抗本体２２を有した装置による切除は、より大きなＲＦ電力を必要としてより深い損傷を生じさせることが知見されている。他方、高い抵抗本体２２を有した装置は、より一様な加熱を行い、従って損傷の制御性を改善する。本体抵抗を高めて付加熱を発生させるので、同じ時間間隔後に同じ組織温度に到達するのに要するＲＦ電力は少なくてもよい。結果的に、高い抵抗本体２２で発生される損傷は通常より深さが小さくなる。一般に、約５００Ω・ｃｍ未満のより低い本体２２の抵抗値は、より深い損傷形状を形成することになる。同様に約５００Ω・ｃｍ以上のより高い本体２２の抵抗は、より浅い損傷形状を形成することになる。本体２２の電気抵抗は、素材の細孔寸法や素材の有孔率や素材の吸水特徴（親水性対疎水性）を特定することで制御される。細孔寸法の特定本体２２における細孔４４の寸法は変えられる。一般に血液酸素飽和や、透析又は超濾過に使用される約０．１μｍより小さな細孔寸法が、本発明に係るイオン輸送のために使用される。高エネルギー電子顕微鏡によって目視されるこれらの小さな細孔は、巨大分子を拘束するが、上述のように加えられたＲＦ場に応答して細孔を通してイオン輸送ができるようにする。より小さな細孔直径では、細孔４４を通した圧力駆動による液体散布を行っても、本体２２内に比較的高い圧力状態が形成されなければイオン輸送を伴いそうもない。血液のマイクロ濾過に一般に使用されるより大きな細孔直径は、本発明に係るイオン輸送にも使用される。光学顕微鏡技術によって見られるこれらのより大きな細孔は、血液細胞を拘束するが、加えられたＲＦ場に応答してイオンを通過できるようにしている。一般に、８μｍ未満の細孔寸法は、大部分の血液細胞が膜を横切るのを阻止するであろう。より大きな細孔直径では、圧力駆動の液体散布も、細孔４４を通過する巨大分子の付随移送も本体２２に対する通常の濾過圧力でより生じやすくなる。形成された血液細胞エレメントに適応できる更に大きな細孔寸法も使用される。しかし、全体的な有孔率や散布率、また本体２２の細孔内への血液細胞の占拠については、細孔寸法の増大に伴ってより考慮に入れなければならない。血液酸素飽和や透析、血漿搬出のような血液濾過の為に使用される在来の多孔で生物学的に適合した膜材は、多孔本体２２としての働きを行うことができる。そのような膜材は、例えば再生セルロース、ナイロン、ポリカーボネット、ポリビニリデンフッ化物(ＰＴＦＥ)、ポリエーテルスルホン、変性アクリル共重合体や酢酸セルロースから造られる。代わりに、(ナイロン、ポリエステル、ポリエチレン、ポリプロピレン、過フッ化炭化水素、細径ステンレススチールや他の繊維等の)素材を所望の細孔寸法と有孔率を有したメッシュに織ることで多孔な又は微細孔を有した素材が製造される。織成素材は、メッシュを織り上げるのに細径の繊維が使用されるので、非常に可撓性に富んでいるために、織成素材を使用するのは有利である。織成素材を使うことで細孔寸法における一様性と一貫性も達成される。スペクトラムメデイカル工業会社（テキサス州ヒューストン）は、２％の有孔率を有した５μｍの細孔寸法を有したナイロンとポリエステルの織成素材を市場に供給している。３０％の有孔率と３μｍの細孔寸法を有したステンレススチールの織成素材も、スペクトラムメディカル工業会社から入手される。テコトのようなメーカも所望の仕様に合致した織成素材を生産している。より小さな細孔寸法を有した織成素材は、素材に基づいて造られる。織成メッシュは、方形織りメッシュ又はあや織りメッシュを含む従来の技術によって製造される。方形織りメッシュは、『垂直二連式』方法によって形成される。あや織りメッシュは、２本の繊維を上下に送って形成される。素材は、チューブや球等の３次元構造に織られる。代わりに、素材は平坦な２次元シートにも織られ、本体２２の所望の３次元形態に（熱成形、熱接合、機械的変形、超音波溶接等で）成形される。細孔寸法は、泡立ち点の計測法を利用して細孔寸法が特定される。泡立ち点の値は、(水吸着特徴が同じであると仮定すれば)主として細孔寸法の関数であって、膜を通るように液体に力を加えるのに必要とされる圧力として定義される。泡立ち点の値を計測するための基準は、ＡＳＴＭＦ３１６−８０である。細孔寸法は、膜の予想液体流抵抗と相関している。一般的な提案として、より大きな細孔は、より多くの液体がより大きい流量で細孔を流れるようにする。同様に、より小さな細孔は細孔を通る液体の散布の容量と割合を制限する。或る点では、細孔は非常に高い圧力時を除外して液体散布を効果的に阻止するのに十分に小さくなっているが、他方それにもかかわらず、イオン輸送が下記の状態で生じ得るようにしている。細孔４４を通した液体散布を少なくしたり、実質的に行わないの方が好ましい。細孔４４を通した液体散布を制限したり実質的に行わない方が幾つかの理由で有利である。第１に、それは高浸透圧溶液を血液溜りに移送することで惹起される塩分や水の過負荷状態を制限できる。高浸透圧溶液が上述のように塩化カリウムを含んでいれば、これは特に当を得ている。更に、細孔４４を通した液体散布を制限したり、実質的に行わないことでイオン輸送が混乱無しに行われる。付随的な液体散布によって邪魔されないことで、イオン輸送における本体２２と組織との中間面に連続的な事実上の電極４８（図８を見よ）を創り出す。事実上の電極４８は、導電金属表面を必要とせずに効率的にＲＦエネルギーを移す。所定の多孔質素材に対するｐｓｉの泡立ち点の値は、更にイオン輸送の特徴を具体化するのを助け、それによって多孔質素材は、組織切除に対する適合性を示すことになる。所定の多孔質素材に対する泡立ち点の値が本体２２を膨らませるのに必要とされる圧力（即ち、膨張圧力）を越すと、素材の細孔４４を通した圧力駆動の流体散布を促進せずに、本体２２をその拡張した形態に圧力で膨らませることができる。本体を膨らませる圧力よりも大きな泡立ち点の値で素材を特定することで、細孔４４を通したイオン輸送が、細孔４４を通る付随的な液体散布無しで、確実に行われることに成る。本体を膨らませる圧力りも大幅に小さい泡立ち点の値は、細孔４４を通した過剰な液体散布のために、多孔質素材を有した本体２２がその目標とした拡張形態に決して到達できなくなることも示すことに成る。他方、多孔質素材の泡立ち点の値は、多孔質素材の引っ張り強度を越すべきでない。泡立ち点の値と引っ張り強度との間のこの関係を特定することによって、液体の散布は、異常に高い圧力が伝播する以前に起きて、本体２２が破裂する危険性を減じることに成る。泡立ち点の値を特定することは、より大きな細孔寸法の素材の使用に対して調停してくれる。より大きな細孔寸法の素材は、膨らみと、膜を通した過剰な流体散布の問題を呈する。有孔率の特定細孔４４の配置と細孔４４の寸法は、本体２２の有孔率を確定する。有孔率は、素材を含んでいない、又は空になっている、又は細孔４４から構成されている本体２２上のスペースを表している。百分率として表現され有孔率は、本体素材によって占拠されていない本体２２の容積百分率を表している。約１０％より大きな有孔率を有した素材に対して、有孔率Ｐ（％で）は、次のように決定される。Ｐ＝１００（１−ρ_b／ρ_m）その場合、ρ_bはその重量と容積によって決定されるような本体２２の密度であり、ρ_mは、本体２２を造っている素材の密度である。約１０％よりも小さな有孔率を有した素材に対して有孔率を得るために、走査式電子顕微鏡が細孔の数とそれらの平均直径を得るために使用される。有孔率Ｐ（％で）は、次に次のように得られる：Ｐ＝Ｎπ（ｄ²／４）その場合：Ｎは、細孔の密度であり、（Ｐ_n／ａ）に等しい。Ｐ_nは、本体２２における細孔の数である。ａは、本体２２の全細孔面積（ｃｍ²）である。 πは、定数で３．１４１６・・・である。ｄは、細孔の平均直径（ｃｍ）である。有孔率の大きさは、上述したように本体２２の液体流れ抵抗に影響する。本体２２の等価電気抵抗は、更にその有孔率に左右される。低い有孔率の素材は、高い電気抵抗を有しており、それに対して高い有孔率素材は、低い電気抵抗を有している。例えば、９％の高浸透圧の溶液（５Ω・ｃｍの抵抗）に晒されると、３％の有孔率を有した素材は、（１５０と４５０Ω・ｃｍの間の）血液又は組織の電気抵抗に匹敵する電気抵抗を有することができる。所定の有孔率に対する細孔４４の分布もイオン輸送の効率に影響する。有孔率の値が与えられた場合、より少ない、しかし、より大きな細孔の配列に代えて、多くのより小さな細孔４４の配列が好ましい。多数の小さな細孔４４が存在すると、各細孔４４における電流密度がより小さくなるように電流密度を配分する。電流密度を減らすと、組織への電気エネルギーのイオン流れが、抵抗熱損失による減少を最小限に留めて生じる。更に、都合の良い大きい流体流抵抗を手助して加えてくれるために、多くのより小さな細孔４４の配列が、より少ない、しかしより大きな細孔の配列に代えて好まれる。多数の小さな細孔４４を設けると、各細孔４４を通して液体散布が生じる割合を制限することになる。本体２２を横切った抵抗の動的変化は、シリコン等の多孔弾性素材から造られた本体２２の直径を変えることでもたらされる。この構成では、弾性本体２２は、弛緩した状態で所定の有孔率を創り出す際に同じ寸法の細孔を弾性材にドリル加工して弾性本体２２を多孔状態にされる。弾性本体２２が膨張されると、その有孔率は基本的に一定のままとなっているが、本体２２の壁厚は減ることになる。かくして、本体２２の直径を増大するに伴って、本体２２の壁厚を減らして表面積を増すために本体２２を横切る抵抗は減る。本体２２の表面積が２の係数だけ増大すると、本体２２の厚さも２の係数だけ減って、結果的に４の係数だけ抵結果的に、所望の損傷形態が本体２２の形態に従って特定される。これで、同じ多孔本体２２を使用して本体２２の形態を制御することで、小さな損傷や浅くて広い損傷や広くて深い損傷を形成できる。好ましくは、多孔本体２２は、所望の切除領域に渡って首尾一貫した細孔寸法と有孔率とを有するべきである。一貫した細孔寸法と有孔率を持たないと、切除領域に渡る本体２２の電気抵抗の差は、より高い電流密度を持った、結果的により高い温度の局部領域を発生させる。もし電気抵抗の差が十分に大きいものであれば、損傷は所望の深さ又は長さに延びることがないので治療に役立たなくなる。更に、本体２２における低い有孔率の一様でない部位は、局部化された加熱作用の結果として自から物理的損傷を被ることになる。吸水特性の特定本体２２の多孔質素材は、疎水性又は親水性のいずれかである。しかし、多孔質素材の吸水特性も素材の電気抵抗に影響する。同じ細孔寸法と有孔率の素材に対して、親水性の素材は、素材を通る液体流量を大幅に増やさなくても無線周波数エネルギーのイオン輸送を行う能力がより大きくなる。媒体中に浮遊しているイオンは、疎水性素材と比較して、素材の泡立ち点の値を越えた駆動圧力がなくとも親水性素材の細孔を一杯に占拠する傾向がより強い。親水性素材の細孔中にこれらイオンが存在することで、細孔を通した流体散布を必要とせずにイオン電流を流す能力を有することになる。結果的に、細孔寸法は、親水性素材に関してはより容易に小さくでき、それによって所望のイオンによる電流搬送能力に悪影響を与えずに泡立ち点の値を高めて液体散布を最少化できる。更に、有孔率と抵抗との間の関係は、親水性素材の場合には疎水性素材の場合よりもより直接的である。幾つかの形のナイロン（例えばナイロン６やナイロン６／６）は、多孔電極として使用するために適した高い吸水性を有した親水性素材の例である。下記の例 −３で同定されたナイロンの例では、６５％の相対湿度と２０℃の温度において４．０％から４．２％の水分吸収率を有している。それにもかかわらず、ＰＥＴやＰｅＢａｘ等の在来の医療グレードの『バルーン』素材は、疎水性である。媒体中のイオンは、疎水性膜の細孔を占めそうにもなく、親水性素材と比較して素材の泡立ち点の値を越した駆動圧力がない。結果的に、疎水性素材は、細孔内にイオンを搬入するのに細孔を通る液体流をより必要とする傾向があり、それによって多孔質素材をよこぎって電気エネルギーを伝えられるようにしている。そのような素材に関しては、本体の膨張圧力は、効果的なイオン輸送をできるようにするために泡立ち点の値を越すべきである。更に、細孔内へのイオン流を制限しようとする疎水性素材のより高い表面張力によって、疎水性素材も親水性素材と比較して細孔における素材破損を惹起するより大きな傾向を示している。疎水性素材における各細孔を横切った大きな電位差は、水分子の分離や、膜素材の誘電性破損や、局部集中した過熱を起こすことになろう。破損は、高温作用に関連しており、素材に応じて細孔を開いて細孔周囲の素材を焼き、一般に素材の質を低下させる。更に、素材の破損は、組織の黒焦げ等、ＣＤ切除と同様な有害な組織作用を生む。従って、より疎水的な特徴からより親水的な性特徴に多孔質素材の吸水特徴を変えることで、細孔寸法や有孔率を変えなくても望ましくない電気的特徴を相殺することができる。例えば、細孔における高い電流密度や電位低下による素材破損の事件は、素材の有孔率を高めることによって減少される。しかし、素材破損の事件は、例えば一般に高い吸水性を有した再生セルロースやナイロン６やナイロン６／６等の親水性素材を選択することによって有孔率を変えること無しに減ぜられる。代わりに、より親水的にするコーティングや表面処理が親水性行の少ない素材に適用される。例えば、幾つかの素材は、特別に調合された親水性コーティングに浸漬されて、紫外光線に晒されて、素材表面にコーティングを結合している。もし、コーティングが質低下を起こさずに切除温度に耐えれば、従来の『バルーン』素材が本体２２用に使用されている場合にそのアプローチは特に役立つ。細孔寸法や有孔率や吸水特徴に寄るところの他の望ましくない電気特徴を相殺するために他の対策が採用される。例えば、より大きな細孔の素材に対しては、又は多孔な親水性素材が使用される場合には、本体２２を横切ぎる流体圧力を制御することによって散布率が制御される。代わりに、より大きな細孔の素材に対しては、又は多孔な親水性素材が使用される場合には、粘度を高めて、これによって散布率を低減する素材が高浸透圧溶液に加えられる。粘度を高めるために加えられる素材の例として、イオンコントラストの（放射線不透過の）素材や、非イオングリセロールや濃縮されたマンニトール溶液が含まれる。例えば、より大きな細孔寸法を有した織成素材の電気性能は、レノグラフィン（登録商標）−７６のようなイオン放射線不透過のコトラスト素材の付加によって補助される。放射線不透過素材を水溶液に加えることによって、本体２２は螢光透視法（コトラスト素材に基づいた超音波心臓透視法）の下で見られる。多孔質素材の流れ抵抗は、媒体の高くなった粘度によって効果的に高くなる。粘度を高めるイオン素材の使用によって、イオン素材の濃度に基づいて膜の抵抗を過度に高める必要がなくなる。次の表−１は織成ナイロンの１３．０ｍｍのディスク検知部によるイオン放射線不透過素材を使った生体外実験での結果を要約している。表−１織成ナイロンディスクによる切除におけるイオンコントラスト素材の効果注意：全ての損傷寸法は、６０℃での退色特徴に基づいている。表−１は、イオンコントラスト媒体が、同等な抵抗結果を達成し且つ所望の損傷を創り出すのに必要とされる電力を低減できることを示している。親水性又は疎水性のいずれかの多孔質素材に対して、本システム１０は、本体と組織との中間面に近接したインピーダンスを検出する装置を備えることができる。図９が示すように、インピーダンスは、散布率の増大にもかかわらずインピーダンスが安定する限度点に到達するまで、液体散布の流量割合の増大と共に低減する。インピーダンスを検出することで、最小流量割合Ｒ_MIN（そこでは、インピーダンスが余りにも高い）と最大流量割合Ｒ_MAX（それ以上では起こり得る塩分又は水分の過負荷状態が存在するようになる）との間で散布流量を制御することができる。本体内の導電性媒体に浸潰された電極３０の表面積は、イオン輸送を高めるために増大される。しかし、本体の小さな形状萎み性や全体的な可撓性等の所望の特徴は、電極寸法に実際的な拘束を課す。本体２２の細孔４４へ電極３０を接近させると、導電媒体を通したイオン輸送の効率も高める。また、可撓で小さな萎んだ形状を示す構造上の特徴は、これを考慮する上での実際上の制約となる。本体２２の形成拡張可能で−萎むことができる本体２２は、ガラス製鋳型の外部又は内部の周りで形成される。この構成では、鋳型の外部寸法は、拡張可能で−萎むことができる本体２２の所望の拡張した形態にマッチしている。鋳型は、所望の壁厚が達成されるまで本体素材の溶液中に所定の手順で浸漬される。鋳型は、次いで成形された拡張可能で−萎むことができる本体２２を残して食刻除去される。代わりに、拡張可能で−萎むことができる本体２２は、更に押し出し成形されたチューブからブロー成形される。この構成では、本体２２は、接着剤又は熱溶着を使って一端でシール結合される。本体２２の他方端は、開放したままになっている。拡張可能で−萎むことができる本体２２は、鋳型の内側に設置される。高圧ガス又は流体等の膨張媒体が、開放したチューブ端から導入される。チューブ状本体２２が鋳型形状を取るように膨らませられると熱に晒される。成形された拡張可能で−萎むことができる本体２２は、次いで鋳型から引き抜かれる。本体２２の有孔率は、炭酸ガスレーザ、エキシマレーザ、ＹＡＧレーザ、高出力ＹＡＧレーザ、電子粒ボンバードメント等によって成形の前後のいずれかで与えられる。以前に説明したように、組織切除のための本体２２の電気特徴を改善するために表面の親水性をより高めるように、コーティングや表面処理も施工される。市場で入手できる多孔質素材も本体２２へと成形される。再生セルロースのような化学工程によって形成される接着性の悪いその種の素材に対して、素材は、浸漬加工（図３２Ａに概略示されており、後で説明する）や、射出成形によって、又は押出し成形中に直径や外形を変えることによって化学的に３次元の形状に成形される。熱接着やレーザ溶接、超音波溶接及び接着剤による接合が行われるそれら素材に対しては、その素材が使われているシートから３次元の形状を成形するために、これらの接着や溶接の技術を使ういろいろな方法がある。据付け物とマンドレルが、熱と圧力とを関連させて本体２２を成形するのに使用される。図１９から２３は、多孔質素材２００を切除用本体２２の所望の３次元の形状に成形する上で好ましい方法を示している。図１９に示すように、シート２００が据付け物２０４上の成形腔所２０２に設置される。成形腔所２０２の形状は、本体２２の末端部に対して所望される形状に対応している。図示の実施例では、その形状はほぼ半球状となっている。図２０が示すように、成形マンドレル２０６はシート２００の一部分２０８を成形腔所２０２内に押し込む。成形マンドレル２０６の形状は、成形腔所２０２の半球形状にマッチしている。マンドレル２０６は、素材部分２０８を間に挟みながら腔所２０２内にしっくりと嵌合する。これで圧力によって所望の半球形状を素材部分２０８にセットする。成形マンドレル２０６か成形腔所２０２のいずれか、又は両方が加熱されて、成形腔所２０２内において素材部分２０８に付加的な熱セットを与えることができる。成形腔所２０２内における圧力と、オプションでの熱は、その素材部分２０８を平坦形状から所望の半球形状に成形する( 図２１を見よ)。先に成形された部分２０８を備えたシートは、据付け物２０４から取外され、仕上げ据付け物２１０（図２２を見よ）上に乗せられる。仕上げ据付け物２１０は、先に成形された部分２０８の形状にマッチした形状を有した末端部２１２を有している。部分２０８は、末端の据付け物端部２１２上にフィットする。仕上げ据付け物２１０は、図示の実施例でも半球状になっているが、本体２２の近位端部に所望されている形状を有した近位端部２１４を備えている。シート２００は、据付け物２１０の近位端部２１４の周りでうまくひだを造ってまとわり着いている。仕上げ据付け物２１０は、周りにおいてシート２００の残りの素材がオーバラップしたプリーツ２１８で集合される基部領域２１６を有している。シート２００は、それによって据付け物２１０の全形状にしっかりと沿うことに成る。仕上げ据付け物２１０は、本体２２の所望の形状を成したシート２００に付加的な熱セットを与える手助けをするために加熱される。成形加工を促進するためにクラムシェルの型（図示されていない）が、更に据付け物２１０の周りに固定される。さて多孔本体２２（図２３を見よ）として成形されたシート素材は、据付け物２１０から滑らして外される。据付け物２１０の基部領域２１６の周りに集められた素材のプリーツ２１８は、例えば熱接着や超音波溶接によって互いに接着される。これで、直径の絞られた首部分２２０を本体２２に形成し、カテーテルチューブの末端への本体２２の取付けを容易にする。プリーツ加工の前に、シート端部２１７は、プリーツ加工中に集まって来る素材量を最小に抑制するために部分部分に切り込まれる。プリーツ加工後は、過剰な素材は、折り返されて首部分２２０に接着され、及び／若しくは、さもなければ、首部分２２０と末端部２０８との間に滑らかな変遷部を形成するように切り取られる。代わりに、据付け物２０４から取り外した後は、先に成形された部分２０８を備えたシート２００は、拡張可能な据付け物２２２（図２４を見よ）の周りに掛け渡される。シート２００の近位端部２１７は、締着部材２２３によって据付け物２２２の首部分の周りにぴったりと締着される。据付け物２２２は、本体２２に必要とされる形状に気体又は液体を使って拡張されるバルーン（例えば、テフロン材から造られた）等から構成されている。それによってシート２００は、所望の形状を取るように拡張する据付け物２２２によって成形される。据付け物２２２の拡張前又は拡張中に、熱がシート２００の端部２１７に加えられ、素材を柔軟にして成形加工を補助する。外部圧力もシート２００の近位端部に加えられ、所望の縮径を成した首部分２２０を造るのを補助する。これによって、更に近位端部２１７で素材が『束になる』のを防ぐ助けをする。据付け物２２２自身は、更に据付け物を拡張するために加熱された気体や液体を使用することによって加熱される。熱は、本体２２の所望の形状にシート２００を付加的に熱セットする。外側のクラムシェルの型（図示されていない）も、成形加工を容易にするために据付け物２２２の周りに固定される。代わりに、食刻で外されるガラス等の素材から成る外側シェルは、所望の最終形状を与えるために使用される。据付け物２０４又は２２２のいずれかを使用して本体２２の成形に使われるいずれの加熱加工に対しても、細孔寸法が加熱加工中に大幅に変化しないようにヒートシンク（図示されていない）が、先に成形された末端部分２０８を冷やすために使用される。代わりに、細孔寸法への加熱の影響は、本体２２への成形以前に第１例におけるシート２００の成形に際して推測され、考慮される。例えば、もし細孔が成形中に開くようであれば、細孔は成形中の寸法増大を考慮に入れるべく製造中に比例的により小さく形成される。かくして、所望の細孔寸法は、シートを本体２２に成形している間に最終的に達成されることになる。成形加工後に、据付け物２２２は収縮されて、引き抜かれる（図２５を見よ）。成形された本体２２２が残る。なおもう一つ別の代替加工（図２６と２７を見よ）では、本体２２は、２つの予じめ成形された部分２２５を周囲のシーム２２４に沿って結合することによって形成される。図示の実施例では、部分２２５は、その周辺周りの余った素材を切除して、図１９から２１に示されたように半球として成形される。部分２２５は、素材の特徴に基づいて、型成形加工によって同様に予じめ成形されることになる。２つの部分２２５を結合するシーム２２４は、素材の性質に基づいて熱接着、超音波溶接、レーザ溶接、接着剤接合、縫合等によって形成される。採用される接着や縫合の方法は、確実にシームが気密で液密な部分を形成するように選択される。シーム２２４の引っ張り強度も、多孔質素材の泡立ち点の値を越すべきである。代わりに、シートから所定寸法に切断された多孔質素材の２つのほぼ円形状の平坦部分が、先行成形を行わずにシームによってそれらの周辺周りで結合される。これで、開放した内部を取囲んだ通常萎んでいるディスクを創り出す。使用中、開放した内部に空気か液体を導入することで、ディスクを本体２２に必要とされる形状に拡張させる。ディスクも、ディスクを所望の形状にさせる内部支持構造体５４（図５から７に概略化されている）を取り囲んでいる。好ましくは、シーム２２４で半球状の又は平坦な部分２２５を結合した後、シーム２２４に対して越えて広がった余った素材は切除される。尚、組織とシーム２２４の幾分粗くなった面部分との接触は外傷を発生させるので、結合された部分２２５は、好ましくは裏返しされる。裏返しで、シーム２２４を（図２８Ｂが示しているように）本体２２の内部に設けることになり、組織との直接接触から遠ざける。図２８Ａが示すように、結合されけた部分２２５は、一端２５２に小さな孔２５０をあけて、引っ張りワイヤ２５４を挿入し、それを他方端２５６に取付け、その他方端２５６をその孔２５０を通して引っ張ることによって裏返される。これで、取付けられた半球状部分２２５を内側を外に返すことになる。上記実施例では、周囲のシーム２２４は、本体２２の軸線周りに延びている。代わりに、（図２９Ａと２９Ｂが示しているように）シーム２２６は、本体２２の軸線に沿って延び、平坦な又は３次元の形に予じめ成形されたいずれかの２つ以上の部分２２８を本体２２に結合することができる。各々が本体部分２２８を支持する嵌合据付け物（図示されていない）が使用され、熱や超音波エネルギーがシーム２２６を造るために加えられている間は部分２２８を静止させておく。図３０が示しているように、他の軸方向に延びたシーム２３０も、シートをもう一つ別のシートに結合するのではなく、むしろシートを区画するために多孔質素材シート内に設けられる。更に、区画された多孔電極についての詳細については後で説明する。図解の目的で、図３０は、シーム２２６、２３０に沿った区画部分の半球状の突出を幾分誇張して示している。好ましくは、結果的に得られた本体２２は丁度説明したように裏返され、軸方向に延びたシーム２２６又は２３０を本体２２の内側に設けるようにしている。図２６から３０に示された部分２２５又は２２８は、平坦な又は３次元形状に予じめ成形されているかを問わず、必ずしも同じ素材から造られる必要が無いことを察知すべきである。異なった多孔特徴の素材は、丁度説明したようにシームによって結合される。代わりに、多孔質素材は、導電性又は電気絶縁性のいずれかである孔の無い素材にシームによって結合される。更に代替構成として、導電素材は、シームによって絶縁素材に結合され、(導電性の)一方が組織に接触し、（電気絶縁性の）他方が血液溜りに露出する二重側部を有した電極本体を提供することができる。事実上、電極本体に関連して使用に適したどんな可撓材も本発明のこの局面に係るシームを使って結合される。更に、複合電極本体を形成するためにシームによって共に結合される部分の数は変えられることも理解すべきである。勿論、色々な具体的な形状も選択される。好適な形状は、基本的には図２が示しているように末端部が球状輪郭を成した球形状で対称形となっている。しかし、非対称または非球状の形状も使用される。例えば、拡張可能で−萎むことができる本体２２は、カテーテルチューブ１２を取付けるために内側に徐々に湾曲したり、首をつくる平坦な末端輪郭で形成される。後で説明するように、図３３と３４Ｂが示しているように細長い円筒形状も使用される。図１０は、代替の拡張可能で−萎むことができる多孔本体５０を示している。この実施例では、本体５０は通常拡張された形態の形状を取るように成形された開放気孔の発泡体から構成されている。電極３０は、発泡本体５０内に取り囲まれている。高浸透圧の液体媒体３８が開放気孔を満たしながら発泡本体５０内に導入され、既に説明したように切除エネルギーの所望のイオン輸送ができるようにしている。発泡本体５０を使用したイオン輸送も、もし本体５０が散布率を制御するために発泡本体５０の有孔率よりも小さい有孔率を与えてくれる外部多孔スキン５１（図１０の右側が示しているように）を備えていれば、実行されることに成る。この構成では、（前に説明したように）摺動シースがカテーテルチューブ１２に沿って前進され、発泡本体５０を萎んだ形態に圧縮する。同様に、シースを引き込めると、圧縮力を取り除く。シースの無くなった発泡本体５０は、跳ねて開き、拡張可能で−萎むことができる本体５０を拡張した形態に戻す。図示された好適な実施例では、末端の操縦機構５２（図１を見よ）は、展開中でも展開後でも多孔質電極構造体２０の操作を高める。操縦機構５２は変更できる。図示の実施例（図１を見よ）では、操縦機構５２は、ハンドル１８によって保持された外部操縦レバー５８に連結された回転カム輪５６を有している。回転輪５６は、左右の操縦ワイヤ６０の近位端を保持している。ワイヤ６０は、切除エネルギー信号ワイヤ３２と共にカテーテルチューブ１２を通って、末端のチューブ端１６に隣接した弾性可撓ワイヤ又はリーフスプリング(図示されていない) の左側と右側に接続している。更に、この詳細と他のタイプの操縦機構が、参考までにこの明細書に組み込まれているランキスト氏とシンプソン氏の米国特許第５，２５４，０８８号に示されている。図１に示されているように、操縦機構５２のリーフスプリングは、カテーテルチューブ１２の末端１６内に支持されている。図１が示しているように、操縦レバー５８を前方に動かすと、一方の操縦ワイヤ６０を引いてリーフスプリングを撓めたり湾曲させ、それと共に末端のカテーテル端１６と電極構造体２０とを一方向に撓めたり湾曲させる。操縦レバー５８を後方に動かすと、他方の操縦ワイヤ６０を引いてリーフスプリング６２を撓めたり湾曲させ、それと共に末端のカテーテル端１６と電極構造体２０とを他方向に撓めたり湾曲させる代わりに、図３２Ｃが示すように、操縦可能なリーフスプリング２６８は、多孔本体２２の末端にそれ自から取り付けられている末端取付け具２７０の一部分である。この構成では、リーフスプリング２６８は、多孔本体２２の内側のチューブ２７２内で末端のカテーテル端を越えて延びている。リーフスプリング２６８に取り付けられた操縦ワイヤ６０、６２も、チューブ２７２を通っている。リーフスプリング２６８の近位端は、末端のカテーテル端１６に取り付けられたハブ２７４に取り付けられている。この構成では、ハンドル１８上の操縦レバー５８の前後移動で、本体２２内においてリーフスプリング２６８を両方向に湾曲させる。リーフスプリング２６８は、末端取付け具２７０を動かし、リーフスプリング２６８が湾曲する方向に多孔本体２２を変形させる。いずれの構成でも、操縦機構５４は、拡張可能で−萎むことができる本体がその萎んだ形態にあっても、その拡張した形態にあっても使用可能である。図３２Ａ、３２Ｂは、末端取付け具２７０とリーフスプリング２６８とを多孔本体２２に取り付ける好適な方法を示している。図３２Ａでは、多孔本体２２は、所望の形状を有した拡張可能な据付け物２７８を再生セルロース２７８の溶液内に浸漬することで形成される。そのような拡張可能な据付け物２７８の詳細は、もう一つ別の文脈で既に説明し、図２４、２５に示した。多孔本体２２は、既に説明したように、色々な他の方法で形成されることを察知するべきである。図３２Ｂが示しているように、据付け物は、近位の首部分２８０と末端の首部分２８２とを有し浸漬形成された多孔本体２２を形成する。本体２２の成形後は、拡張可能な据付け物２７６は、図３２Ｂも示しているように、萎まされて引き抜かれる。図３２Ｂが示しているように、末端の首部分２８２は、例えば接着剤を使って、又は接着剤接合や熱接合、機械的接合、ネジ、巻き付け、又はこれらのいずれかの組合わせによって取り付けられるスリーブ２８８を使って、末端の取付け具２７０の周りに取り付けられる。取付け具２７０は、既に説明したように、それに予じめ取り付けられたリーフスプリング２６８と、関連した構成要素とを有している。最初取付け具２７０に取り付けられると、本体２２の近位の首部分２８０は、リーフスプリング２６８の反対側の方向に向けられる。末端の首部分２８２を取付け具２７０に取り付けた後、本体２２は、図３２Ｃが示すようにリーフスプリング２６８を覆うように末端の取付け具２７０の周りで裏返しされる。リーフスプリング２６８の近位端は、末端のカテーテル端１６によって支持されたハブ２７４に取付けられている。裏返された近位の首部分２８０は、次いでスリーブ２８６を使用して末端のカテーテル端に取付けられる。スリーブ２８６は、接着剤接合や熱接合、機械的接合、ネジ、巻き付け、又はこれらのいずれかの組合わせを含んだ色々な方法でカテーテルチューブの周りに取り付けられる。多孔電極本体をカテーテルの末端に取り付ける色々な代替方法は、『チューブと電線を拡張可能で−萎むことができる構造体に取付ける幹部エレメント』(弁理士ラベル２４５６Ａ−６)の名称の同時係属特許出願に開示されている。後でより詳細に説明するように、末端の取付け具２７０は、多孔本体２２上の孔の無い導電部分としての働きもできる。同様な取付け具２７０は、同じ目的のために多孔本体２２上の他の場所に配置される。探針（図示されていない）も、リーフスプリング２６８の代わりに又は組合わせて末端の取付け具２７０に取り付けられる。そこから、探針は本体２２（裏返しに続く）の内側において、カテーテルチューブ１２を通ってハンドル１８上の適当な押し−引き制御器（図示されていない）まで延びている。探針はカテーテルチューブ１２の軸線に沿って移動可能となっており、末端の取付け具２７０上で軸方向に押し引きされ、それによって本体２２を伸ばしたり、又は短縮する。更に、電極本体への末端の取付け具の取り付けに関する詳細は、『末端で操縦又は操作する拡張可能で−萎むことができる電極構造体』(弁理士ラベル２４５８Ａ−４)の名称の同時係属特許出願に示されている。図３３と３３Ａ／３３Ｂは、図示のように末端の取付け具に組み合わされ且つ図３２Ｂと３２Ｃに示されているように、末端のカテーテル端１６に取り付けられる細長くて円筒状の例示的な電極本体を示している。図３３では、本体２９０は、末端と近位の首部分２８０と２８２を形成するために、半径を変えて押出しや浸漬や型成形によって細長い形状に成形される。適当な末端の取付け具２７０（仮想線で示されている）が、末端の首部分２８２内に取付けられており、細長い本体２２は、図３２Ｂと３２Ｃに示されれているように裏返されて組立体を完成する。近位の首部分２８０は、次いで図３２Ｃに示されているように末端のカテーテル端１６に取り付けられている。図３４Ａと３４Ｂでは、本体２２は、（図３４Ｂに示されているように）一様な半径で押出し成形や型成形や浸漬によって形成された素材のチューブ２９２から形成されている。この構成（図３４Ｂを見よ）では、以前に開示されているように形成されたシーム２９４は、チューブ２９２の末端を閉じている。チューブ２９２の近位端は、末端のカテーテル端１６に取付けるために管状孔２９６の周りでシールされる。代わりに、チューブ２９２の末端は、（図３４Ｂで仮想線で示されている）末端の取付け具２７０の周りでシールされる。後者の場合、チューブ２９２は、カテーテルの末端１６に取り付ける前に末端の取付け具２７０の周りで裏返しにされる。本体の多孔領域を限定する細孔４４のパターンは変えられる。好ましくは、図２と３に概略示されているように、拡張可能で−萎むことができる本体２２の少なくとも近位側の１／３の表面部分は、細孔４４が無い状態となっている。拡張可能で−萎むことができる本体２２の少なくとも近位側の１／３の表面部分上に細孔４４を設けていないのは、幾つかの理由で望ましい。この部分は、通常組織とは接触しておらず、その結果、事実上の電極境界が存在していても、何んの目的も果たしていない。更に、この部分も一番小さな直径を示している。もし電気的に導通するものであれば、この部分は、望ましくない最大の電流密度を有することになる。通常組織接触を行っていない最小直径の近位部分を細孔４４の無い状態にしておくことで、組織接触をすることになる拡張可能で−萎むことができる本体２２の末端部分において又はその近くで最大の電流密度が確実に分配されるようにする。本体２２の末端部分が組織と端部接触するように向けられて切除が行われるものと予測される場合、多孔領域は、勿論拡張可能で−萎むことができる本体２２の末端部の先端の周りに向けられるべきである。この端部に臨む向き合わせのために、多孔領域は、図２と３が示しているように、本体２２の末端部１／３から１／２に被せられ連続したキャップから構成される。しかし、組織との末端部接触が企図されている場合、好適な実施例（図１１を見よ）では、導電多孔領域は本体２２の末端部先端周りの同心状の『雄牛の目』パターンで配列された別々のエネルギー伝達ゾーン６２に区画される。本体２２の側部領域を組織と接触するように向きを合わせして切除が行われるものと予測される場合、多孔領域は、本体の末端部１／３から１／２の周りで周方向に隔設された軸方向の細長いエネルギー伝達ゾーン６２（図１２を見よ）に好ましくは区画される。多孔領域が本体２２上の区画されたゾーン６２から構成されると、内部でグループを成したシールされた気のう６４（図１３を見よ）が個別に液体３８を各多孔領域区画部６２に搬送する為に使用される。各気のう６４は、個別に管腔６６と連通しており、それが担当している一つの多孔区画部６２の導電液を受け取る。多数の気のう６４は、更に、幾つかの、しかし全部の気のう６４ではないが液体で選択的に膨らませることで、膨らんだ本体２２の形状をより具体的に制御する能力も与えてくれるものである。気のう６４は、別々に成形されて本体２２内に挿入されるか、又はそれらは、拡張可能で−萎むことができる本体２２を型成形している間に一体的に形成される。図１２が示しているように、区画された多孔ゾーン６２は、更に拡張可能で− 萎むことができる本体２２の萎みに関連して使用するのにも良く適合している。この構成では、無孔電極は、ひだのある又は折り目のある領域６８から構成されている。これらの領域６８を創り出すために、本体２２の型は、拡張可能で萎むことができる素材が所望の領域６８に沿って若干より薄く形成されたり、凹み付けされたり、リブ付けされるように予じめ成形された表面形状を有している。拡張可能で−萎むことができる本体２２は、一貫して一様に本体２２を自からの上に周方向で萎ませながら、これらのひだのある領域６８の周りで萎む。かくして、結果的に生じる萎んだ形状は、より一様で且つコンパクトにされる。図１２に示されている萎み可能な本体２２も、多孔領域の他のパターンにも使用されることを察知すべきである。ひだのある領域６８には、更にもし必要ならば細孔も設けられる。図１４は、二重の作用を果たす拡張可能で萎むことができる電極構造体７０の実施例を示している。構造体７０は、前に説明したように内部電極３０を収容した拡張可能で萎むことができる本体２２を有している。本体２２は、導電流体３８を収容しており、また更に丁度説明したように電気エネルギーのイオン輸送を可能にする一つ以上の多孔領域６２も有している。図１４に示されている構造体７０は、更に本体２２の表面上に一つ以上の導電領域７２も有している。（図１４が示しているような）一実施例では、孔の無い導電領域７２は、スパッターリングや、蒸着や、イオンビーム被覆や、沈着された種層を覆う電子メッキや、又はこれらの加工の組合わせによって拡張可能で− 萎むことができる本体２２上に被覆される金、プラチナ、プラチナ／イリジウムなどの金属から構成される。代わりに、孔の無い導電領域７２は、本体の表面に固定された薄い箔からも構成される。更に代わりに、孔の無い導電領域７２は、１箇所以上で多孔本体２２によって支持された（図３２Ｃに示された末端の取付け具のような）硬質な取付け物からも構成される。本体２２内の信号ワイヤ（図示されていない）は、無孔電極に電気的に接続されている。信号ワイヤは、ハンドル１８によって保持されたコネクター３８に接続するためにカテーテルチューブ１２を通っている。好適な実施例（図１５を見よ）では、孔の無い導電領域７２は本体の内部に通されて電気接続部の所望の点で、本体２２を貫いて蛇行された絶縁信号ワイヤ２６から構成されている。蛇行貫通されたワイヤ２６の末端部の電気絶縁は除去され、導電領域７２としての働きをするように好ましくは平坦化される電線部分を露出する。平坦化された領域では、導電接着剤７３によって本体２２に固定取り付けされる。接着剤７３は、更に好ましくはワイヤ２６が通っている本体２２の領域にも塗られてそれをシールする。同じ信号ワイヤ２６は、多数回に渡って本体２２を貫通して蛇行されて、必要に応じて多数の領域７２を形成する。無孔電極７２と、関連した信号ワイヤとを拡張可能で−萎むことができる電極本体２２に取り付ける色々な方法については、『電極構造体の向上された電気接続』(弁理士ラベル２４５８Ａ−５)の名称の同時係属特許出願に説明されている。無孔電極７２は、心筋組織における電気的活動を検出するのに使用される。検出された電気的活動は、外科医による分析のための電位を処理する外部制御器に送られる。その処理によって、潜在的な不整脈の病巣を特定するために電位又は消極事象のマップが作られる。無孔電極７２で一旦特定されると、多孔領域６２は、病巣を切除するために前に説明したように無線周波数エネルギーを送るために使用される。代わりに、又は電気的活動の検出との組合わせで、無孔電極７２は、ペース信号を送るために使用される。このように、無孔電極はペースマッピング又は同調化マッピングを実施できる。好ましくは(図１６を見よ)、本体２２の表面は、単極又は双極の検出に又はペース取りに適した電極１００を保持している。これらの電極１００は、本体２２の内側表面上に配置されているが、検出や又はペース取りのためのそれらの作用は、本体２２の良好な導電特徴の理由で害されることはない。異なった電極の設置が、単極又は双極の検出に又はペース取りのために使用される。例えば、対になった２−ｍｍの長さで１−ｍｍの幅の電極が本体２２の内側表面上に設けられる。接続ワイヤ１０２がこれらの電極１００に取り付けられる。高浸透圧の溶液がこれらの電極を短絡させるのを防ぐために、それには、( 例えばエポキシや接着剤等の)電気絶縁材１０４で覆われなければならない。好ましくは、電極間の距離は約１ｍｍで、確実に良好な双極の活動電位図が得られるようにしている。これら内部電極の好ましい設置箇所は、構造体２２の末端部の先端と中心とである。更に、多数のゾーンが使用される場合は、切除領域間に電極を設けるのが望ましい。外科医が本装置を螢光透視法の下で目標とする部位に案内できるように不透明なマーカー１０６を本体２２の内側表面上に設けるのも望ましい。この目的には、いずれの高原子重量材も適している。例えば、プラチナやプラチナ／イリジウムがマーカー１０６を作るのに使用される。これらのマーカー１０６の好ましい設置箇所は、構造体２２の末端部の先端と中心である。それによって、図１４に示されている拡張可能で−萎むことができる構造体７０は、『固体の』無孔電極７２の使用を『液体の』又は多孔な電極６２と組合わせている。拡張可能で−萎むことができる構造体は、一つの電極作用を使う治療目的のために心筋組織のマッピングと、異なった電極作用を使う治療目的のために心筋組織の切除とを実施可能にする。代替実施例では、構造体７０の無孔電極７２は、無線周波数エネルギーを送って組織を切除するために多孔領域６２と共に直列状態で使用される。この構成では、領域７２を受け持つ信号ワイヤは、発生器４０に電気的に接続されており、一つ以上の領域７２による伝達のために無線周波数エネルギーを搬送する。同時に、内部電極３０は、多孔本体を通る媒体３８による伝達のために無線周波数エネルギーを受け取る。領域７２を取囲んでいる多孔構造体を横切ってイオン輸送を行うことで、切除電極の有効表面面積を拡げる。この実施例では、図１４に示されている拡張可能で−萎むことができる構造体７０は、それで検出とマッピングのために第１の有効表面面積を有した電極７２の使用を組合わせている。第１の有効表面面積は、電極７２を取り囲んだ多孔構造体を横切って高浸透圧液体のイオン輸送を行うことによって切除を行う切除目的の為に選択的に増大される。もし液体散布が細孔を通って行われれば、内部電極３０は、それら領域の有効電極表面面積を増大するように要求されることはない。それら領域が無線周波数エネルギーを伝達する時に行われる細孔を通したイオン媒体の液体散布は、それ自身それら領域７２の有効な伝達表面面積を増大するのに十分な働きをする。しかし、もしイオン輸送が実質的に液体散布無しで行われれば、無線周波数が伝達のために外部領域７２に供給されている時と同時に内部電極３０を使用して無線周波数エネルギーを伝達することも有利になると思われる。この実施例では、領域７２はそれら自身多孔導電材から造られることも知るべきである。このように、イオン輸送は、領域７２自身を横切って行われ得る。前に説明したように(図１を見よ)、制御器３２は、好ましくは、発生器３０から本体２２内に支持された電極への無線周波数切除エネルギーの搬送を制御している。好適な実施例（図２を見よ）では、多孔電極構造体２０は、制御器３２に接続された１つ以上の温度検出エレメント１０４を保持している。温度検出エレメント１０４は、サーミスターやサーモカップル、又はその種の形をしている。温度検出エレメント１０４は、電極構造体２０の外部と熱伝導接触しており、切除中に構造体２０の外側の組織の状況を検出する。温度検出エレメント１０４によって検出された温度は、制御器３２によって処理される。入力された温度に基づいて、制御器３２は電極３０による無線周波数エネルギー伝達の時間と電力レベルとを調節し、所望の損傷パターンと他の切除目的を達成する。温度検出エレメント１０４を拡張可能で−萎むことができる電極本体に取り入れる色々な方法については、『電極構造体用の向上された電気接続』(弁理士ラベル２４５８Ａ−５)の名称の同時係属特許出願に説明されている。図３１Ａ、３１Ｂと３１Ｃに示すように、温度検出エレメント１０４は、更にシート２６０、２６２を本体２２に共に結合しているシーム２５８の近くに又はその内部に配置される。そのようなシーム２５８の形成については、既に説明したし、更に図２６から３０に示している。図３１Ａと３１Ｂに示されているように、各温度検出エレメント１０４は、一方のシート２６０上に設置され、次いで他方のシート２６２によって覆われる。２枚のシート２６０、２６２は、次いで共に接合されて本体２２を形成する。シーム２５８は、検出エレメントを包囲している。各検出エレメント１０４の信号ワイヤ２６４は、図３１Ａと３１Ｂが示しているように、シート２６０、２６２の外部までシーム２５８の無い所を延びている。前に説明したように、本体２２は好ましくは裏返される(図２８Ａを見よ)。図３１Ｃが示すように、裏返しでシーム２５８と包囲された信号ワイヤ２６４の両方を本体２２の内部に設けることになる。信号ワイヤ２６４は、制御器３２に接続するために首部分２６６に通されている。温度検出エレメント１０４の代わりに又はそれに加えて、ペース用電極と検出用電極を、図３１Ａから図３１Ｃに示されているように、裏返された電極本体２２のシーム２５８内に包囲することもできる。そのような構成では、裏返し後に、本体素材と組織との間に企図した接触が行われる素材表面に接近したシーム内にそれらが配置されるように電極を位置決めするのが好ましい。更に、多くの温度検出エレメントを使って制御される多くの切除エネルギーの伝達器の使用についての詳細は、１９９４年８月８日に出願され且つ『多くの温度検出エレメントを使用して組織切除を制御するシステムと方法』の名称の同時係属米国特許出願番号第０８／２８６，９３０号に開示されている。例−１生体外での分析３つの電極構成について分析された：（１）分子量のカットオフを１２，０００−１４，０００ドルトンとし且つ内部液体媒体として９％の塩水溶液を使用して（スペクトラによって製造された）再生セルロースから造られた透析チューブから構成された１３ｍｍディスク状本体を有した本発明に係る多孔な拡張可能で−萎むことができる電極構造体、（２）１３ｍｍの直径を有したスパッタリングされたプラチナのディスク状の電極本体と、（３）１０ｍｍの直径を有したアルミ箔製の拡張可能で−萎むことができる半球状電極構造体である。高温の温度条件が存在した領域において、動物（羊）の組織内に０．５ｍｍだけサーミスターが埋め込まれた。電極（１）、（２）に対して、最高温度がエッジ加熱効果によってディスク状本体のエッジに発生した。電極（３）に対しては、最高温度が電流密度の最も大きい半球状本体の末端部の先端で発生した。無線周波数の電磁電力は、サーミスター温度を６０℃、７０℃、８０℃又は９０℃に維持するように調整された。全ての損傷の直径は、組織の脱色をマークする６０℃の等温線に基づいて計測された。次の表−２は、生体外での分析で観察された結果をリストアップしている。表−２注意：ＴＭは、損傷が経壁であって、深さが実際には計測値よりも大きかったことを示している。多孔電極構造体（１）は、電極（２）のような正規の金属切除電極と比較して対流式冷却によって最小限の影響しか受けなかった。これは、特定の損傷発生中に流体流量を変え、且つ多孔電極構造体に関してサーミスター温度を維持するのに何ら電力を変化させる必要が無い事を観察して分かった。表−２は、組織温度に基づいて電力を調節する場合に、多孔電極構造体が、金属被覆された電極構造体と少なくとも同じくらい大きく損傷を創り出したのを示している。多孔電極構造体は、更に金属被覆された電極構造体と比較してリーズナブルなインピーダンスレベルを有していた。この例は、多孔電極構造体が心外膜の、心内膜の又は壁内の基質を切除するために制御された状態で１．０ｃｍより深い損傷を創り出すことができることを示している。多孔電極構造体を形成する透析チューブは、高い吸水特徴を有している。透析チューブは水に晒されると大幅により可撓的になる。分子量のカットオフは、１２，０００から１４，０００ドルトンであった。より大きな又はより小さな分子量のカットオフについてはスペクトラム社から入手できる。テストされる透析チューブに対する分子量カットオフから予測細孔寸法への変換は、『透析／超濾過』の名称の医療器具小冊子９４／９５（ｐ１０）から得られるように、１００，０００ドルトンは０．０１μｍに等しく、５０，０００ドルトンは０．００４μ ｍに等しく、１０，０００ドルトンは０．００２５μｍに等しく、５，０００ドルトンは０．００１５μｍに等しくなっている。透析チューブは、小さな細孔寸法にもかかわらず親水特徴と大きい有孔率を有している。結果的に、泡立ち点の値は非常に高く、また抵抗は無線周波数エネルギーの供給中に液体流を必要としない程度に十分に低いものとなっている。例−２有限要素分析３次元の有限要素モデルが、２８．４ｍｍの全長で、６．４ｍｍの直径で０．１ｍｍの本体壁厚の細長い形状を有した多孔電極構造体に対して創られた。０．２ｍｍの直径の金属ワイヤが、ＲＦエネルギー源に接続された内部電極としての働きをするように本体の長さに沿って内部に延ばされた。本体は、５．０Ω・ｃｍの電気抵抗を有した９％の高浸透圧溶液が充満された。構造体の多孔本体が、電線として作られた。心臓組織とのしっかりとした接触が、電極の下方の平面に横たわっている電極本体の全長に沿って確保された。血液との接触が、電極の上方平面に横たわっている電極本体の全長に渡って確保された。血液領域と組織領域は、各々１５０と５００Ω・ｃｍの抵抗を有していた。電極本体に対して、１．２ｋ−Ω・ｃｍと１２ｋ−Ω・ｃｍの抵抗に基づいて分析が行われた。表３は、ＲＦ切除電力が電極の多孔本体に対して色々な電力レベルで、また色々な抵抗レベルで多孔電極に加えられた時の最高組織温度の深さを示している。表−３図１７は、多孔本体が１．２ｋ−Ω・ｃｍの抵抗を有している場合、電極に５８ワットで２４０秒間電力が加えられた時の温度プロフィールを示している。図１７における５０℃の等温線の深さは１．４ｃｍである。図１８は、多孔本体が１２ｋ−Ω・ｃｍの抵抗を有している場合、電極に４０ワットで２４０秒間電力が加えられた時の温度プロフィールを示している。図１８における５０℃の等温線の深さは１．０ｃｍである。全ての場合、最高温度は、組織と細長い多孔構造体の両端エッジとの間の中間面に位置している。これは、多孔本体の細長い形状に対する温度検出エレメントの好適な場所は、本体の各端部エッジである。好ましくは、各エッジは、少なくとも一つの温度検出エレメントを保持すべきであり、多数の温度検出エレメントは、少なくともそれらの一つが組織に確実に面向するように対角状に対向した側に配置されるべきである。データは、更には、金属面電極で観察されるように最も高温な領域が、組織内に深くは移動され無いことも示している。最も高温な領域は、直接検出のために組織−電極本体の中間面に一貫して存在している。幾分より大きい差が、計装する或る他の局面において遭遇されるのであるが、この特長は、検出された温度と事実上最も高温な組織温度との間の差をできれば理論的に０℃に削減することになる。なるより高い抵抗を有した本体を備えた多孔な電極本体（図１８を見よ）は、より低い抵抗値（図１７を見よ）を有した多孔な本体に比較して見たところ、より一様な温度プロフィールを発生した。電極本体の抵抗を高めたことで組織−電極本体の中間面で発生された付加的加熱の熱によって、同じ最高温度に到達するのに必要とされた電力はより少ないものであった。結果は、損傷深さが浅くなったことであった。以前に説明したように、本体２２の抵抗を選択することによって、外科医は、損傷形状に大きな影響を与えることができる。小さな抵抗の本体２２を使用することで、結果的により深い損傷を発生させるが、またその反対も起きる。次の表 −４は、経験的なデータに基づいて、本体抵抗と損傷深さとの間の関係を説明している。表−４多孔電極構造体の削減された熱伝導率によって、無孔金属面電極と比較すると、損傷形成は、電極周りの動的な血液流状況に対して感度が小さいものと予測される。多孔電極を介した切除エネルギーの供給は、特に浅い心房用損傷が要求される時に所望の損傷特徴を得るためにより精密に制御される。次の表−５は、経験的なデータに基ずいており、血液流量における変化によって対流式冷却条件に対する多孔電極構造体の感度低下を証明している。表−５多孔な電極構造体を使用することで、構造上の長所が与えられる。それは、金属の導電シェルを拡張可能で−萎むことができる本体の外側に設置することで関連事象として起こり得る付着についての問題点を切り離してくれることである。多孔電極構造体も、外部の導電材への組織の付着が起り得る潜在的な問題も回避してくれる。これらの構造上の長所に加えて、切除作業の温度制御が改善される。組織を切除するのに在来の金属電極を使うと、組織−電極の中間面は、取囲んでいる血液流によって対流式で冷却される。これらの対流式冷却作用に依って、最高組織温度の領域は、組織においてより深く位置される。結果的に、金属電極エレメントに関連した検出エレメントによって検出された温度条件は、実際の最高組織温度を直接的に反映していない。この状況下では、最高組織温度の条件は、実際の検出された温度から推断され、予測されなければならない。多孔電極構造体２０又は７０を使用して、周囲の血液流によって組織−電極の中間面を対流で冷却するのを最小へと減ずる。結果的に、最高温度の領域は、組織と多孔電極との間の中間面に位置されることになる。結果的に多孔電極エレメントに関連した検出エレメントによって検出された温度条件は、より精密に実際の最高の組織温度を反映することになる。例−３生体外の実験が、親水性素材（Ｈｐｈｉ）対疎水性素材（Ｈｐｈｂ）を多孔組織切除エレメントとしてそれらを使った項目で比較するために実施された。表− ６は、その結果を要約している。表−６多孔質切除材の要約注意：『素材破損』は、上述したように素材の破損が存在することである。表−６は、細孔寸法が親水性素材を使用して小さくされ、それによって多孔質素材を通した液体散布を最小限にし、又は停止し、他方依然として膜を通してイオン輸送ができるようにしておることを証明している。疎水性多孔質素材は、高い抵抗の多孔電極を実現できるようにする。他方、親水性多孔質素材は、低い抵抗の多孔電極を実現できるようにする。所望の損傷特徴を得る上記表が証明しているように、同じ拡張可能で−萎むことができる多孔電極構造体２０は、広くて浅い又は大きくて深いいずれかの損傷を選択的に形成できる。色々な方法論が、この結果を得るべく無線周波数エネルギーの供給を制御する為に使用される。Ａ．Ｄ50C作用一つの代表実施例では、制御器（コントローラー）２は、外科医から（ｉ）所望の損傷が生存可能な組織と生存不可能な組織との間の境界深さまで組織−電極の中間面の下で広がる範囲、及び／若しくは（ｉｉ）組織−電極の中間面と境界深さの間の損傷内で発生される最高組織温度の項目における所望の治療結果を受け取る入力部３００（図１を見よ）を制御器４２は有している。制御器４２は、更に、損傷境界深さや切除電力レベル、切除時間、実際の表面下の組織温度及び電極温度の間において観察された関係を相関させる関数を保持する処理エレメント３０２（図１を見よ）を有している。処理エレメント３０２は、所望の治療結果をその関数と比較し、その比較に基ずいて操作条件を選択して、上記の実際の又は予測された表面下の組織温度を越さずに所望の治療結果をを達成する。処理エレメント３０２によって選択された操作条件は、切除電力レベルの制御や切除時間の選択された目標切除時間への制限、上記最大切除電力レベルを受ける切除電力レベルの制限、及び／若しくは領域４４と組織との間の所望の百分率の接触の予測を含んだ本体２２の多孔領域４４の向き等の切除工程の色々な局面を制御できる。処理エレメント３０２は、実際の最高組織温度を検出する為に組織内に入り込んで拡張可能で−萎むことができる構造体２０によって保持された又は他にはそれに関連した温度センサーに依存している。代わりに、処理エレメント３０２は、操作条件に基ずいて最高組織温度を予測できる。好適な代表実施例では、電極構造体２０は、領域４４の熱塊の瞬間的な局部温度（Ｔ１）を検出少なくとも一つの温度検出エレメント１０を保持している。或る時間における温度Ｔ１は、発生器４０によって電極３０に供給される電力の関数である。損傷の特徴は、Ｄ50Cと呼ばれる５０℃の等温領域の組織面下の深さの表現で表現される。深さＤ50Cは、多孔領域４４の物理的特徴（即ち、その電気と熱の伝導率と抵抗と寸法）と；組織と多孔領域４４との間の接触百分率と；領域４４の熱塊の局部温度Ｔ１と；内部電極３０によって伝達されるＲＦ電力の大きさ（Ｐ）と；組織がＲＦ電力に晒される時間（ｔ）の関数でる。所望の損傷深さＤ50Cに対して、安全について更に考慮するとマトリックスにリストアップされた操作条件中における最適操作条件の選択を拘束することになる。原則的な安全上の拘束条件は、最高組織温度ＴＭＡＸと最高電力レベルＰＭＡＸである。最高組織温度条件ＴＭＡＸは、深くて広い損傷を与えるのに十分に高いが（一般に約８５℃と９５℃との間）然し安全上約１００℃未満で、組織乾燥や組織微細破裂を起こすことが知られている温度範囲以内に入っていることである。ＴＭＡＸは、中間面とＤ50Cとの間の電極−組織の中間面の下方の或る距離の所で生じることが認識されている。最高電力レベルＰＭＡＸは、内部電極３０の物理的特徴とＲＦ発生器４０の発電能力とを考慮している。これらの関係は、上記例が図解しているように、制御された実際のまた模擬実験される条件下で経験的に及び／若しくはコンピュータモデルによって観察される。或る多孔領域４４に対するＤ50C作用は、上記値のマトリックスにリストアップされている全て又は幾つかの表現や、経験的なデータ及び／若しくはコンピュータによるモデル化から引き出されたそれらの関係表現で表現される。処理エレメント３０２は、上述のようにｔ＝１２０秒とＴＭＡＸ＝９５℃に対してまた一連の他の操作条件に対してＤ50C温度境界関数を定義するこのマトリックスの操作条件をメモリーに有している。外科医は、更に、上記の識別符号を使用して構造体２０の特徴を識別し、所望の最大ＲＦ電力レベルＰＭＡＸや；所望の時間ｔや；所望の最高組織温度ＴＭＡＸを設定するのに入力部３００も使用する。これらの入力に基ずいて、処理エレメント３０２は、所望の治療結果をマトリックスに定義されている関数と比較する。発生器４２は、関数の変数を制御して上記ＴＭＡＸを越さずに所望の治療結果を達成するように操作条件を選択する。それで、この構成は、外科医が事実上所望のＤ50Cを特定することで『ダイアルで損傷』形成できるようにする。更に、Ｄ50C作用を引き出す詳細と、所望の損傷パターンを得る為のそれの使用とは、ここに参考までに組み込まれている『本体組織の切除中に所望の損傷特徴を得るシステムと方法』の名称で、１９９５年５月１日出願の係属米国出願番号第０８／４３１，７９０号に見ることができる。Ｂ．区画された領域：デュティサイクル制御色々なＲＦエネルギー制御方法が、図１１（ゾーンの軸方向に隔設された雄牛の目パターン）と図１２（周囲方向に隔設されたゾーン）とに示されている区画された多孔パターンと関連して使用される。説明目的に、（電極領域とも呼ばれている）４４は、Ｅ（Ｊ）で符号表示されるが、Ｊは或るゾーン４４（Ｊ＝１からＮ）を表示している。前に説明したように、各電極領域Ｅ（Ｊ）は、Ｊが或るゾーン４４を表し且つＫが各ゾーン上の温度検出エレメントの数（Ｋ＝１からＭ）を表しているＳ（Ｊ、Ｋ）で表示される少なくとも一つの温度検出エレメント１０４を有している。このモードでは、デュティサイクル１／Ｎの多数のパルスでＲＦ電力を供給するように適当な電力切り替え中間面を介して条件設定される。パルス化された電力供給で、各個別の電極領域Ｅ（Ｊ）に送られる電力量（Ｐ_E(J) ）は次のように表現される。Ｐ_E(J)αＡＭＰ_E(J) ²×ＤＵＴＹＣＹＣＬＥ_E(J) その場合：ＡＭＰ_E(J)は、電極領域Ｅ（Ｊ）に送られるＲＦ電圧の振幅であり、ＤＵＴＹＣＹＣＬＥ_E(J)は、次のように表現されるパルスのデュティサイクルである：ＤＵＴＹＣＹＣＬＥ_E(J)＝ＴＯＮ_E(J)／（ＴＯＮ_E(J)＋ＴＯＦＦ_E(J)）その場合：ＴＯＮ_E(J)は、各パルス期間中に電極領域Ｅ（Ｊ）がエネルギーを発する時間であり、ＴＯＦＦ_E(J)は、各パルス期間中に電極領域Ｅ（Ｊ）がエネルギーを発しない時間である。式（ＴＯＮ_E(J)＋ＴＯＦＦ_E(J)）は、各電極領域Ｅ（Ｊ）に対するパルス期間を表している。このモードでは、発生器４０は、各電極領域に対して１／Ｎのデュティサイクル（ＤＵＴＹＣＹＣＬＥ_E(J)）集中的に発生できる発生器４０は、前のパルスのデュティサイクルの終わりが次のパルスのデュティサイクルの始めに若干重なるように隣接電極領域に対して連続した電力パルスを順番に発生する。パルスのデュティサイクルにおけるこの重なりは、なんら中断期間が連続した電極領域間でパルス切り替え中に解放回路によって生じないようにして確実に発生器４０が連続的に電力を供給できるようにするものである。このモードでは、温度制御器４２は、各電極領域（ＡＭＰ_E(J)）のＲＦ電圧の振幅に対して個々に調節を行い、それ発生器４０によって制御されてデュティサイクル中に各電極領域に送られる切除エネルギーの電力Ｐ_E(J)を個別に切り替える。このモードでは、発生器４０は、連続したデータ獲得サンプリング期間に循環する。各サンプリング期間中には、発生器４０は、個々のセンサーＳ（Ｊ、Ｋ）と、制御器４２によって出力されるような検出エレメント１０４によって検出された温度符号ＴＥＭＰ（Ｊ）（Ｓ（Ｊ、Ｋ）の内最も高いもの）とを選択する。一つより多い検出エレメント１０４が或る電極領域に関連している場合(例えばエッジに位置した検出エレメントが使用される場合)、制御器４２は或る電極領域に対して全ての検出された温度を登録し、これらの内からＴＥＭＰ（Ｊ）を構成する最も高い検出温度を選択する。このモードでは、発生器４０は、各データ獲得期間中に各電極Ｅ（Ｊ）で局部的に検出された温度ＴＥＭＰ（Ｊ）を外科医によって確立された設定点温度ＴＥＭＰSETと比較する。この比較に基ずいて、発生器４０は、その電極領域と全ての他の電極領域に対してＤＵＴＹＣＹＣＬＥ_E(J)を維持している間に、電極領域Ｅ（Ｊ）に供給されたＲＦ電圧の振幅ＡＭＰ_E(J)を変え、設定点温度ＴＥＭＰ_SE _T にＴＥＭＰ（Ｊ）を発生して維持する。設定点温度ＴＥＭＰSETは、外科医の判断と経験的なデータに応じて変わり得る。心臓切除の為の代表的な設定点温度ＴＥＭＰは、７０℃が代表的な好ましい値であるが、４０℃から９５℃の範囲にあると思われる。発生器４０がＡＭＰ_E(J)を制御する方式は、比例制御方法、比例積分導出（ＰＩＤ）制御方法又はあいまい理論制御方法を採用できる。例えば、比例制御方法を使用して、もし第１検出エレメントによって検出された温度がＴＥＭＰ（１）＞ＴＥＭＰ_SETであれば、発生器３０によって発生された制御信号が第１電極領域Ｅ（１）に加えられるＲＦ電圧の振幅ＡＭＰ_E(1)を低減するが、他方で第１電極領域Ｅ（１）に対するデュティサイクルＤＵＴＹＣＹＣＬＥ_E(1)を同じに維持している。もし第２検出エレメントＴＥＭＰ（２）によって検出された温度がＴＥＭＰ（２）＜ＴＥＭＰ_SETであれば、発生器３０の制御信号は、第２電極領域Ｅ（２）に加えられるパルスの振幅ＡＭＰ_E(2)を増加するが、他方で第２電極領域Ｅ（２）に対するデュティサイクルＤＵＴＹＣＹＣＬＥ_E(2)をデュティサイクルＤＵＴＹＣＹＣＬＥ_E(1)などと同じに維持している。もし或る検出エレメントによって検出された温度が設定点温度ＴＥＭＰ_SETにあれば、関連した電極領域に対してＲＦ電圧の振幅になんら変化を発生させない。発生器４０は、連続したデータ獲得期間中に電圧差入力を連続的に処理して各電極領域Ｅ（Ｊ）においてＡＭＰ_E(J)を個々に調節するが、他方で集合的なデュティサイクルを全ての電極領域Ｅ（Ｊ）に対して同じに維持している。このように、そのモードは、温度の所望の一様な状態を切除エレメントの長さに渡って維持している。比例積分微分（ＰＩＤ）制御技術を使用して、発生器は、或るサンプリング期間で生じる瞬間的な変化ばかりではなく前のサンプリング期間で生じた変化とこれらの変化が時間経過に伴って変化する割合も考慮に入れている。かくして、ＰＩＤ制御技術を使用して、前の瞬間的な差に比較して差がより大きく成るのか小さく成るのかに基ずいて、また前のサンプリング期間以来差が変化している割合がより大きく成っているのか小さく成っているのかに基ずいて、発生器は、ＴＥＭＰ（Ｊ）とＴＥＭＰ_SETとの間の或る比例して大きい瞬間的な差に異なって反応する。更に、温度検出に基ずいて区画された電極領域に対して個別に振幅の／集合的なデュティサイクルを制御する詳細については、ここに参考までに組み込まれている『多数の温度検出エレメントを使用して組織切除を制御するシステムと方法』の名称で、１９９５年５月１２日出願の係属米国出願番号第０８／４３９，８２４号に見ることができる。Ｃ．区画された領域：差分温度での不能化この制御モードでは、制御器４２は、各データ獲得位相の終わりにその位相に対して最高（ＴＥＭＰ_SMAX）と成っている検出された温度を選択する。制御器４２は、更に、最低（ＴＥＭＰ_SMIN）と成っている検出された温度をその位相に対して選択する。発生器は、選択された最も高い検出温度ＴＥＭＰ_SMAXを選択された高い設定点温度ＴＥＭＰ_HISETと比較する。その比較で、比例、ＰＩＤ又はあいまい理論制御方法を使用して、全ての電極領域に対してＲＦ電圧の振幅を集中的に調節する制御信号を発生する。比例制御実施計画では：（ｉ）もしＴＥＭＰ_SMAX＞ＴＥＭＰ_HISETであれば、制御信号は全ての領域に送られるＲＦ電圧の振幅を集中的に減ずる。（ｉｉ）もしＴＥＭＰ_SMAX＜ＴＥＭＰ_HISETであれば、制御信号は全ての領域に送られるＲＦ電圧の振幅を集中的に増大する。（ｉｉｉ）もしＴＥＭＰ_SMAX＝ＴＥＭＰ_HISETであれば、全ての領域に送られるＲＦ電圧の振幅になんら変化が無い。発生器は、振幅制御の目的に検出温度ＴＥＭＰ_SMAX、ＴＥＭＰ_SMIN又は間の温度のいずれか一つを選択してこの温度条件を予め選択された温度条件と比較できることを察知すべきである。発生器は、或る局部温度ＴＥＭＰ（Ｊ）とＴＥＭＰ_SMIN間の差に基ずいて領域への電力供給を制御する。この実行で、局部検出温度ＴＥＭＰ（Ｊ）とＴＥＭＰ_SMIN 間の差を演算し、この差を選択された設定点温度差ΔＴＥＭＰSETと比較する。そので、電極領域への電力供給を制御する制御信号を発生する。もし或る電極領域Ｅ（Ｊ）に対する局部温度ＴＥＭＰ（Ｊ）が、ΔＴＥＭＰ_SE _T と同じだけ又は（即ち、もしＴＥＭＰ（Ｊ）−ＴＥＭＰ_SMIN≧ΔＴＥＭＰ_SETであれば）ΔＴＥＭＰ_SETより大きく最低の検出された温度ＴＥＭＰ_SMINを越せば、発生器は、或る所定の領域Ｅ（Ｊ）への電力供給を遮断する。ＴＥＭＰ（Ｊ）−ＴＥＭＰ_SM _IN ＜ΔＴＥＭＰ_SETの場合、発生器はその或る所定の領域Ｅ（Ｊ）への電力供給を復帰させる。代わりに、ＴＥＭＰ（Ｊ）とＴＥＭＰ_SMINを比較する代わりに、発生器は、ＴＥＭＰ_SMAXとＴＥＭＰ_SMINを比較することができる。ＴＥＭＰ_SMAXとＴＥＭＰ_SM _IN との間の差が所定量ΔＴＥＭＰ_SETに等しいか、又は越えている場合、発生器は、ＴＥＭＰ_SMINが存在している領域を除いて全ての領域を遮断する。ＴＥＭＰ_SMAX とＴＥＭＰ_SMINとの間の温度差がΔＴＥＭＰ_SETより小さい場合に、発生器３０はこれらの領域を復帰させる。更に、差分温度での不能化を使用する詳細については、ここに参考までに組み込まれている『多数の温度検出エレメントを使用して組織切除を制御するシステムと方法』の名称で、１９９４年８月８日出願の係属米国特許出願番号第０８／２８６，９３０号に見ることができる。Ｄ．ＰＩＤ制御多孔質電極構造体に関しては、血液溜りによる対流冷却の最小限の作用で、予想された温度に代えて、最高組織温度ＴＭＡＸとして実際の検出された温度条件を使用できるようにしている。これによって、そのような構造体も自ら比例積分導出（ＰＩＤ）制御技術を使用している。これら電極構造体に関連して利用可能な図解のＰＩＤ制御技術は、『監視と制御の為に時間で変わる設定点温度曲線を使用する組織加熱と切除システムと方法』の名称で、１９９４年６月２７日出願の係属米国特許出願番号第０８／２６６，０２３号に開示されている。最後に、多孔な拡張可能で−萎むことができる本体内部に配置された内部電極３０は、心臓内の心筋組織のマッピングの為に使用され得ることを察知すべきである。この使用で、内部電極は、例えば電位又は抵抗の形を取ることができる心臓内部の電気的な活動を検出する。検出された電気的な活動は、外科医によって分析される検出された活動を処理する外部制御器に送られる。更に、多孔な拡張可能で−萎むことができる本体内部に配置された内部電極３０は、ペース取り信号を送る為に代わりとして、又は電気的な活動の検出と組み合わせて使用され得ることを察知すべきである。このように、内部電極３０は、ペースマッピング又は同調化マッピングを実行できる。本発明の色々な特長は、次の請求の範囲に述べられている。DETAILED DESCRIPTION OF THE INVENTION Related application This application has a name of "cardiac mapping and ablation system" which is 19 U.S. Patent Application Serial No. 07 / 951,72, filed September 25, 1992, and pending. No. 8 which has a large surface that becomes flat during introduction into the heart U.S. filed July 30, 1993 under the name "Cardiac Resection Catheter" It is a partially pending application of patent application number 08 / 099,994. Field of the invention The present invention generally relates to electrode structures that are deployed inside the body. More specifically The present invention relates to an electrode deployable in the heart for diagnosing and treating conditions of heart disease. Regarding the structure. Background of the Invention Treatment of cardiac arrhythmias depends on the specific physiology of the arrhythmia being treated. That can create tissue damage with various and different geometrical shapes and features Poles are needed. For example, a conventional 8F diameter / 4 mm long cardiac ablation electrode would be approximately 0.5 c m with a depth of about 10 mm and a width of 0.2 cm^ThreeLoss with a damage volume of up to It can transmit radio frequency energy to create wounds in myocardial tissue. These small, shallow injuries are needed in the sinus node to perform sinus node remodeling, Or along the AV groove for various ancillary incisions or atrial spasm (AFL) Along the slow zone of the tricuspid valve gorge for incision or for AV nodal slow pathway incision Is required. However, to remove substrates for gastrointestinal tachycardia (VT), At least 1 cm at a depth greater than 2.0 cm at penetration depth^ThreeHas a damage volume of It appears to require significantly greater and deeper damage. In addition, the need to create relatively large surface area lesions at shallow depths remains I have. One solution proposed to create a variety of damage features is a different form of cutting. The use of energy removal. However, microwaves, lasers and ultrasonics Peripheral techniques surrounding excised or chemically resected are generally tested for this purpose. Not tested. How to actively cool in connection with the transmission of DC and radio frequency ablation energy Employing is to force the interface between the electrode and the tissue to a lower temperature It is known. As a result, the hottest tissue temperature region is shifted further in the tissue. The next step is to better align the borders of It will shift deeply. Actively cooled electrodes are actively cooled Not to transmit more ablation energy into tissue compared to the same electrode used. However, it is known that tissue dehydration and tissue boiling occur. Active cooling control is needed to safely maintain the highest tissue temperature below 00 ° C Is done. To create greater damage in either surface area and / or depth Another solution proposed in is a substantially better solution than is available on the market. The use of large electrodes. However, the larger electrode itself, dimensions and operation Have several problems with gender, and can be too heavy to insert large electrodes through veins or arteries. It will prevent safe and easy introduction into the organs. Selectively create lesions with different geometric shapes and features There is a need for a multipurpose cardiac ablation electrode. Multi-purpose electrodes can safely and easily It will have the necessary flexibility and operability to be able to be introduced into the device. Once the mind When deployed inside the gut, these electrodes, in a controlled manner, have large, deep losses. For wounds, small and shallow injuries, and large and shallow injuries depending on the treatment needed It has the ability to fire enough energy to create it. Summary of the Invention The present invention provides for the ionic transport of electrical energy without substantially spraying a liquid. Various porous electrodes used in tissue ablation systems An assembly is provided. The perforated electrode assembly embodying the features of the present invention has an outer area surrounding the inner area. It has a surrounding wall. Lumen inside the medium containing ions Convey to the area. One element converts the medium in the inner area to a source of electrical energy Is bound to. In accordance with one aspect of the present invention, at least a portion of the wall is comprised of a medium contained in a medium. Consists of a porous material sized to allow macromolecules to pass while allowing on passage Have been. This allows the wall to pass electrical energy through the porous material to the exterior of the wall. To transport ions. According to another aspect of the present invention, at least a portion of the wall comprises a porous material. Large enough to allow the ions contained in the medium to pass without substantial liquid spraying. It is composed of a porous material. Thereby, the wall sprays liquid substantially throughout the wall Ion transport of electrical energy through the porous material to the outside of the wall without I am able to do it. According to another aspect of the present invention, at least a portion of the wall is included in the medium. Composed of a porous material sized to allow It allows ion transport of electrical energy through the material to the outside of the wall. Book According to this aspect of the invention, the porous material has a bubble point value greater than the internal pressure. Have. According to another aspect of the present invention, at least a portion of the wall is included in the medium. Composed of a hydrophilic porous material sized to allow To enable ion transport of electric energy to the outside of the wall through the porous material I have. According to this aspect of the invention, the porous material foams more than the internal pressure. Has a point value, thereby substantially eliminating liquid spraying in the porous material. Even ion transport occurs. Other features and advantages of the invention are set forth in the following description and drawings. BRIEF DESCRIPTION OF THE FIGURES FIG. 1 illustrates a heart with an expandable porous electrode structure embodying features of the present invention. 1 is a plan view of a tissue resection system. FIG. 2 shows the electrode structure in its expanded configuration, the system shown in FIG. FIG. 3 is an enlarged side elevational view of a partially broken porous electrode structure used in connection with the system. . Figure 3 shows the electrode structure in its collapsed form, the porous electrode shown in Figure 2; FIG. 4 is an enlarged side elevation view of the structure. FIG. 4 is a partially broken and further enlarged view of the porous electrode structure shown in FIG. FIG. 4 is a somewhat schematic side view. FIG. 5 illustrates the expansion of the electrode structure due to the presence of the internal elongated flexure support structure. Porous electrode used in connection with the system shown in FIG. FIG. 4 is an enlarged side elevation view of a pole structure partially broken. FIG. 6 shows the electrode structure in its collapsed form by manipulating the outer sliding sheath. FIG. 6 is an enlarged side sectional view of the porous electrode structure shown in FIG. 5. FIG. 7 illustrates that the electrode structure can be moved by the presence of an internal interwoven mesh support structure. The multiple used in connection with the system shown in FIG. 1 is shown in expanded form. FIG. 4 is an enlarged side elevational view of a partially broken porous electrode structure. FIG. 8 shows the ionic current density across the pores of the electrode body shown in FIG. FIG. 8 is a somewhat schematic enlarged view taken and enlarged substantially along line 8-8 of FIG. You. FIG. 9 shows the detected impedance and the impedance through the pores of the electrode body shown in FIG. It is the graph which showed the relationship between ON transport. FIG. 10 shows an electrode structure composed of a porous foam in an enlarged form. , An alternative porous electrode structure used in connection with the system shown in FIG. FIG. 4 is an enlarged side elevational view of a partially broken portion of FIG. FIG. 11 shows the pores of the structure arranged at the end of the body in a bull's eye pattern. The array of porous electrode structures used in connection with the system shown in FIG. It is an enlarged side view. FIG. 12 shows that the pores of the structure are circumferentially spaced along the sides of the body. Porous electrode structure used in connection with the system shown in FIG. 1 arranged in a state It is an enlarged side view of a body. FIG. 13 shows a number of chambers for transferring liquid to the partitioned pore areas shown in FIG. FIG. 7 is a side view of a partially broken view showing the use of a. FIG. 14 shows the system shown in FIG. 1 further holding a non-porous electrode element. FIG. 4 is an enlarged side elevation view of a porous electrode structure used in connection with FIG. FIG. 15 shows an electrode element formed by wires meandering through a structural body. FIG. 5 is an enlarged side sectional view of a porous electrode structure that also holds the porous electrode structure. FIG. 16 shows an enlarged side of a porous electrode structure with internal pace distribution / detection electrodes. It is an elevation view. 17 and 18 relate to the porous electrode structure when operated under different conditions. The tissue temperature profile is displayed graphically. FIG. 19 shows a hemispherical shape from the flat sheet of the porous material to the end of the porous electrode body. FIG. 4 is a somewhat schematic view of the fixture and mandrel to form. FIG. 20 shows a process of forming a hemispherical terminal end shape with a flat sheet of a porous material. FIG. 20 is a side cross-sectional view of the fixture and mandrel shown in FIG. 19; FIG. 21 is an enlarged side cross-sectional view of the porous material sheet after molding of the outer shape of the hemispheric end portion. is there. FIG. 22 shows a portion of the preformed sheet shown in FIG. 21 near the porous electrode body. FIG. 3 is a diagrammatic representation of a finishing fixture for forming a hemispherical shape at the distal end; You. FIG. 23 shows a porous electrode after being formed by the apparatus shown in FIGS. It is an elevational view of a main body. FIG. 24 shows a portion of the preformed sheet shown in FIG. 21 near the porous electrode body. Instead of the finishing fixture shown in FIG. FIG. 3 is a diagrammatic representation of the expandable finishing fixture used. FIG. 25 shows the porosity after being formed by the expandable fixture shown in FIG. FIG. 3 is an elevation view of a quality electrode main body. FIG. 26 shows two of the porous electrode bodies before being joined together to the composite porous electrode body. FIG. 4 shows, somewhat schematically, two preformed hemispherical body portions. FIG. 27 joins the two hemispherical parts shown in FIG. 26 along the perimeter seam It is a side elevational view of the composite-type porous electrode main body formed by this. FIG. 28A provides a peripheral seam inside the body to prevent direct contact with tissue In order to achieve this, the side view of the porous electrode body shown in FIG. FIG. FIG. 28B shows FIG. 2 after it has been turned over to provide a perimeter seam inside the body. FIG. 8 is a side sectional view of the porous electrode body shown in FIG. 7. FIG. 29A illustrates joining two hemispherical portions along an axial seam to form an axial seam. Side section of a porous electrode body formed after turning over to provide the inside of the body FIG. FIG. 29B shows a porous electrode with the inverted axial seam shown in FIG. 29A. It is a top view of a main body. FIG. 30 shows the joining of two hemispherical sections along the main axial seam and an additional intermediate axis. Partition the body with the directional seams, turn them over, and then place those axial seams inside the body. It is a top view of the porous electrode main body formed by cutting. FIG. 31A shows that two sheets of porous material are joined together to form an electrode body. The seam before turning over the body that enclosed the temperature sensing element inside the seam FIG. 5 is an enlarged side sectional view of FIG. FIG. 31B shows the body prior to turning over the body surrounding the temperature sensing element within its seam. FIG. 31B is a side elevation view of the seam coupling body partially shown in FIG. 31A. FIG. 31C shows the seam and the signal wire of the temperature detection element in the main body after turning over. FIG. 31B is a side sectional view of the main body shown in FIG. 31B provided on the side. FIG. 32A shows a regenerated cellulosic material by immersion using an expandable fixture. FIG. 3 is a diagram schematically showing a porous electrode body formed from the above. FIG. 32B illustrates the installation with the expandable fixture removed and the steering assembly removed. The dip formed in FIG. 32A after attaching to the end of the body and before turning over 3 shows a molded body. FIG. 32C illustrates the end fixture and steering assembly shown in FIG. 32B after turning over. 2 shows a dip-formed body provided. FIG. 33 shows the narrowing of the radius along the length to form a distal region and a proximal neck region. FIG. 3 illustrates an exemplary porous body shaped into a long cylindrical outer shape. FIG. 34A shows a tube shaped as an elongated cylinder with a constant radius along its length. FIG. 6 illustrates another exemplary porous body that has been removed. FIG. 34B, for closing the end by a seam and attaching it to a catheter tube 34A shows the tube shown in FIG. 34A sealing the boat tube at the proximal end. are doing. The present invention may be embodied in several forms without departing from its spirit or essential characteristics. Things. The technical scope of the present invention is not limited to the specific scope described in the claims. Rather than described, they are defined in the appended claims. Therefore, All embodiments which come within the meaning and range of equivalency of the claimed invention are embraced by the appended claims. Is what is done. Description of the preferred embodiment FIG. 1 illustrates a tissue resection system 10 embodying features of the present invention. Book Stem 10 includes a flexible catheter tube 12 having a proximal end 14 and a distal end 16. Have. Proximal end 14 includes handle 18. Terminal 16 is An electrode structure 20 embodying the features is provided. The purpose of the electrode structure 20 is It transfers energy. As best shown in FIGS. 2 and 3, the electrode structure 20 is expandable- The main body 22 has an openable main body 22. The outer shape of the main body 22 is in a collapsed form (FIG. 3) And an expanded or expanded configuration (FIG. 2). Illustrated preferred In one embodiment, the expandable and retractable body 22 is inflated and expanded. Liquid pressure is used to maintain the configuration. In this configuration (see FIG. 2), the catheter tube 12 moves along its length. It has an internal lumen 34. The distal end of the lumen 34 is expandable-wither It is open to the hollow interior of the body 22. The proximal end of the inner lumen 34 is Port 36 (see FIG. 1). Liquid expansion medium (arrow 3 in FIG. 2) 8) is carried through the port 36 into the lumen 34 under positive pressure. The liquid medium 38 , Expandable-fills the interior of the body 22 which can be deflated. The liquid medium 38 Department The body 22 that is expandable and deflated under pressure can be retracted from its deflated form. This feature allows the expandable and collapsible body 22 to be guided into the venous structure. When inserted, the withered low profile (ideally less than 8 French diameters, ie about 0 . 267 cm). Once in the desired position When placed, the expandable-withdrawable body 22 can be, for example, about 7-20 mm. Is converted to a fully expanded form. As shown in FIGS. 5 to 7, the structure 20 can be used to extend the body 22 if necessary. To increase or replace the internal pressure of the liquid medium to maintain it. An internal support structure 54 that is normally open and capable of withering can be provided. Inside The shape of the partial support 54 can be changed. It can be, for example, as shown in FIG. The assembly of the flexible elongate element 24 and the internal porosity as shown in FIG. It is also composed of a simple woven mesh and an open porous foam structure 26. In these configurations (see FIG. 6), expandable-withering supported from the inside The main body 22 includes an outer sheath 28 that slides along the catheter tube 12. (See FIG. 6) after removal of the expansion medium by the external compression force applied by It is converted into a form. As shown in FIG. Is advanced over the expandable and collapsible body 22. Extensible -The retractable body 22 retracts to its low profile configuration inside the sheath 28. Shi Expandable by withdrawing the source 28 (see Figure 5 or 7)-withering Pull it away from the main body 22 where it can be made. Release from restraint by sheath 48 When activated, the inner support structure 54 opens with spring force and is expandable-wither. The returnable body 22 is returned to its expanded configuration and receives a liquid medium. As best shown in FIG. 4, the structure 20 further includes an internal electrode 3 made of a conductive material. 0 is provided inside the main body 22. The material of the internal electrode 30 has a relatively high conductivity. And relatively high thermal conductivity. Materials with these characteristics include gold , Platinum, platinum / iridium and the like. Noble metals are preferred. An insulated signal wire 32 is connected to the electrode 30. The signal wire 32 Out of the electrode 30 through the catheter tube and onto the handle 18 (see FIG. 1). To the connector 38. The connector 38 generates the radio frequency of the electrode 30. vessel 40 is electrically connected. In the preferred illustrated embodiment (see FIG. 1), the unit integrated into the controller 42 Or as an independent matching box to the RF generator 40 in either of them Are combined. The controller 42 controls the electrode 30 according to a pre-established standard. Control the supply of radio frequency energy. Further, in this aspect of the system 10, Details will be described later. According to the present invention, the liquid medium 38 used to fill the body 22 is a conductive liquid. Body. Liquid 38 forms a conductive path that carries radio frequency energy from electrode 30. To achieve. Relatedly, body 22 has pores 44 on at least a portion of its surface. Made of a non-conductive thermoplastic or elastic material. Pores of porous body 22 44 (shown diagrammatically in enlarged form in FIG. 4 for illustration purposes) The ablation energy from the body is ion-transported through the conductive medium 38 to the tissue outside the body. Let Preferably, the liquid 38 reduces ohmic losses in the body 22 and thus It has a small resistance to reduce the heating effect of the arm. In the preferred embodiment shown, The liquid 38 also serves at least in part as an additional medium for inflation of the body. U. The components of the conductive liquid 38 can be varied. In the preferred embodiment shown, the liquid 38 is High osmotic pressure with a saturated or near-saturated sodium chloride concentration of about 9% by weight per volume It consists of salt water. High osmotic pressure salt water has a blood resistance of about 150Ωcm and Only about 5 Ω · cm lower than myocardial tissue resistance of about 500 Ω · cm Has become. The component of the conductive liquid 38 is composed of a high osmotic pressure potassium chloride solution. This medium facilitates the desired ion transport, but is used to prevent potassium overload. The speed at which on-transport passes through the pores 44 needs to be monitored more closely. High osmotic pressure The ion transport rate is less than about 10 mEq / min when a potassium chloride solution of It is desirable to keep. As just described, the present system 10 is useful for ablation of myocardial tissue in the heart. Ideally suited. In this embodiment, the surgeon enters the ventricle through the vena cava or artery. The catheter tube 12 is moved until the electrode structure 20 is expanded. The active-retractable body 22 is in its low profile configuration. Once desired An expandable and retractable body 22 within the ventricle expands into its expanded configuration. When tensioned, the area having the pores 44 is brought into contact with the target area of the tissue in the heart. Be extended. For the most part, due to the difference in mass concentration across the pores 44, the ions in the medium 38 will Thus, they will pass through the pores 44 due to the diffusion caused. Pore 44 Diffusion through continues as long as the concentration gradient is maintained across body 22. Pore 4 The ions contained in 4 provide a means to conduct current across body 22. Radio frequency energy is controlled by a controller 42 to generate It is transported to 30. When a radio frequency (RF) voltage is applied to the electrode 30, the current It is carried by the ions in the pores 44. The ions are young during the application of the RF frequency. Move back and forth, but by ions, as occurs if a DC voltage is applied. The RF current provided does not cause any net diffusion of ions. R added This ionic motion (and current flow) in response to the F field causes the medium 3 No need to spray 8 liquids. The ions return radio frequency energy through the pores 44 to the tissue facing the electrode. Carrying in, the return electrode is typically an external patch electrode (forming a unipolar structure) ing. Instead, the transmitted energy passes through tissue (forming a bipolar structure). Can pass through adjacent electrodes in the ventricle. Most radio frequency energy is The tissue is pneumatically heated to form a therapeutic lesion. The electrical resistance of the body 22 has a significant effect on the shape and controllability of the damage. Low Ablation with a device having a resistive body 22 requires more RF power and It has been found to cause deep damage. On the other hand, it had a high resistance body 22 The device provides for more uniform heating and thus improved damage control. High body resistance To generate additional heat, so it is necessary to reach the same tissue temperature after the same time interval. The required RF power may be small. As a result, damage caused by the high resistance body 22 Is smaller than normal. In general, lower body 22 resistance values of less than about 500 ohm-cm It will form a shape. Similarly, a higher body 22 of about 500 Ω · cm or more The resistance will form a shallower damage feature. The electrical resistance of the main body 22 depends on the pore size of the material, the porosity of the material, and the water absorption characteristics of the material (parent material). (Aqueous vs. hydrophobic). Specify pore size The size of the pores 44 in the body 22 can be varied. In general, blood oxygen saturation and dialysis Or about 0. 0 used for ultrafiltration. The pore size smaller than 1 μm is Used for transportation. These visible by high energy electron microscope Small pores bind macromolecules but respond to the applied RF field as described above To allow ion transport through the pores. For smaller pore diameters, Even if the liquid is sprayed by pressure driving through the hole 44, a relatively high pressure If a force state is not formed, it is unlikely to involve ion transport. The larger pore diameters commonly used for microfiltration of blood are in accordance with the present invention. Also used for ion transport. These larger than seen by light microscopy techniques Small pores bind blood cells but allow ions to pass in response to the applied RF field. I am able to do it. In general, pore sizes less than 8 μm indicate that most blood cells Will be prevented from crossing. For larger pore diameters, pressure driven liquid spraying Nor the concomitant transport of macromolecules through the pores 44 nor the normal filtration pressure on the body 22 Is more likely to occur. Larger pore sizes can also be used to accommodate the formed blood cell elements . However, the overall porosity and dispersal rate and the occupation of blood cells in the pores of the body 22 Must be taken into account as the pore size increases. Conventional porosity used for hemofiltration such as blood oxygen saturation, dialysis, and plasma export The biologically compatible membrane material can act as a porous body 22. Such membrane materials include, for example, regenerated cellulose, nylon, polycarbonate, Vinylidene fluoride (PTFE), polyether sulfone, modified acrylic copolymer And made from cellulose acetate. Instead, use nylon, polyester, polyethylene, polypropylene, Material (such as hydrogenated hydrocarbons, small diameter stainless steel and other fibers) to the desired pore size Weave into a porous or microporous material by weaving it with a porosity mesh. It is. Woven materials use non-woven fibers to weave the mesh. The use of a woven material is advantageous because it is always flexible. Woven material The use of also achieves uniformity and consistency in pore size. Spectrum Medical Industries (Houston, TX) has a 2% perforation Nylon and Polyester Woven Materials with 5μm Pore Size To supply. Stainless steel with a porosity of 30% and a pore size of 3 μm Woven textiles are also obtained from Spectrum Medical Industries. It's tekoto Una manufacturers also produce woven materials that meet desired specifications. Smaller pore size The woven material with the method is made based on the material. Woven mesh is based on conventional techniques, including square or twill mesh. Therefore, it is manufactured. The square woven mesh is formed by the "vertical twin" method You. The twill mesh is formed by feeding two fibers up and down. The material is Woven into a three-dimensional structure such as a ball or sphere. Alternatively, the material could be a flat 2D sheet Woven into the desired three-dimensional form of the body 22 (thermoforming, thermal bonding, mechanical deformation, ultrasonic (Formed by welding). The pore size is specified by using a method of measuring a bubble point. Bubble point The value is primarily a function of pore size (assuming the same water adsorption characteristics). , Defined as the pressure required to apply a force to the liquid through the membrane. The criterion for measuring the value of the bubble point is ASTM F316-80. The pore size correlates with the expected liquid flow resistance of the membrane. As a general suggestion, more Large pores allow more liquid to flow through the pores at a higher flow rate. same As such, smaller pores limit the volume and rate of liquid spray through the pores. Some point The pores are sufficient to effectively block liquid spray except at very high pressures. However, ion transport is nevertheless produced in the following conditions: I am trying to make it. It is preferable to reduce or substantially not spray the liquid through the pores 44. . The reason for limiting or substantially not spraying liquid through the pores 44 is for several reasons. It is advantageous. First, it is triggered by transferring the hypertonic solution to the blood pool. Salt and water overload conditions can be limited. The high osmotic pressure solution is M This is especially true if it contains Further, by restricting or substantially eliminating liquid spray through the pores 44, Transport is carried out without confusion. By not being disturbed by incidental liquid spray, A continuous virtual electrode 48 (FIG. 4) is continuous at the interface between the body 22 and the tissue in ion transport. 8). Effective electrode 48 is efficient without the need for a conductive metal surface RF energy is transferred. The psi bubble point value for a given porous material may further characterize ion transport. Help to materialize, so that the porous material is compatible with tissue resection Will be. The bubble point value for a given porous material is required to inflate the body 22 Pressure (ie, the expansion pressure), the pressure-driven fluid through the material pores 44 The body 22 can be pressure inflated to its expanded configuration without promoting spreading. You. By specifying the material with a value of the bubble point larger than the pressure that inflates the main body, Ion transport through the pores 44 is assured without incidental liquid spray through the pores 44 Will be performed. The value of the bubble point at which the pressure for inflating the main body is significantly small is determined by the The main body 22 having a porous material is used to expand the liquid in order to spray excess liquid. Will never be reachable. On the other hand, the value of the bubble point of the porous material should exceed the tensile strength of the porous material. Absent. By identifying this relationship between the value of the bubble point and the tensile strength, Spraying of liquid can occur before the abnormally high pressure propagates, causing the body 22 to burst. This reduces the ruggedness. Specifying the value of the bubble point can be adjusted for the use of larger pore size materials. Will stop. Larger pore size materials can cause swelling and excess fluid through the membrane Presents a spraying problem. Determination of porosity The arrangement of the pores 44 and the dimensions of the pores 44 determine the porosity of the body 22. The porosity is , Free of material, or empty, or composed of pores 44 The space on the main body 22 is shown. The porosity, expressed as a percentage, is To Thus, the volume percentage of the unoccupied main body 22 is shown. For a material having a porosity greater than about 10%, the porosity P (in%) is Is determined as follows. P = 100 (1-ρ_b/ Ρ_m) In that case, ρ_bIs the density of the body 22 as determined by its weight and volume And ρ_mIs the density of the material from which the body 22 is made. Scanning to obtain porosity for material with porosity less than about 10% A scanning electron microscope is used to obtain the number of pores and their average diameter. Porosity P (In%) is then obtained as follows: P = Nπ (d^Two/ 4) In that case: N is the pore density and (P_n/ A). P_nIs the number of pores in the body 22. a is the total pore area of the main body 22 (cm^Two). π is a constant of 3.1416. d is the average diameter (cm) of the pores. The magnitude of the porosity affects the liquid flow resistance of the main body 22 as described above. Body The equivalent electrical resistance of 22 further depends on its porosity. Low porosity materials are high High porosity materials have a low electrical resistance ing. For example, when exposed to a 9% hyperosmotic solution (5 Ω · cm resistance), Material with a porosity of 5% is between blood and tissue (between 150 and 450 ohm-cm). It can have an electrical resistance comparable to the electrical resistance. The distribution of pores 44 for a given porosity also affects the efficiency of ion transport. Porosity Given the value of, instead of an array of fewer, but larger pores, An array of many smaller pores 44 is preferred. There are many small pores 44 Then, the current density is distributed so that the current density in each of the pores 44 becomes smaller. As the current density is reduced, the ionic flow of electrical energy to the tissue is Occurs with minimal reduction. In addition, there is a lot of work to help add a convenient large fluid flow resistance. An array of smaller pores 44 replaces an array of fewer but larger pores. Preferred. When a large number of small pores 44 are provided, a liquid is sprayed through each of the pores 44. This limits the rate at which it can be twisted. The dynamic change in resistance across the body 22 is made from a porous elastic material such as silicon. It is provided by changing the diameter of the main body 22. In this configuration, the elastic body 22 When creating a predetermined porosity in the relaxed state, drill holes of the same size into the elastic material The elastic body 22 is made porous by processing. When the elastic body 22 is expanded, The porosity remains essentially constant, but the wall thickness of the body 22 will decrease . Thus, as the diameter of the body 22 is increased, the wall thickness of the body 22 is reduced and displayed. The resistance across the body 22 to increase the area is reduced. The surface area of the body 22 is a factor of 2. As the load increases, the thickness of the body 22 also decreases by a factor of two, resulting in a resistance of four. As a result, a desired damage form is specified according to the form of the main body 22. Now, By controlling the shape of the main body 22 using the multi-porous main body 22, small damage and shallow Can form wide and deep damages. Preferably, the porous body 22 has a consistent pore size over the desired ablation area. And porosity. Ablation without consistent pore size and porosity The difference in the electrical resistance of the body 22 over the region is higher with a higher current density. Generate local areas with higher temperatures. If the difference in electrical resistance is large enough If the damage does not extend to the desired depth or length, it is useless for treatment . In addition, the low porosity non-uniform portions of the body 22 may be localized heating effects. As a result of the use, they will suffer physical damage from themselves. Identification of water absorption characteristics The porous material of the main body 22 is either hydrophobic or hydrophilic. But porous The water absorption properties of a quality material also affect the electrical resistance of the material. For materials of the same pore size and porosity, the hydrophilic material is the liquid flow rate through the material Greater ability to transport radio frequency energy ions without significantly increasing It will be good. Ions suspended in the medium cause foaming of the material compared to hydrophobic materials. There is a tendency that the pores of the hydrophilic material are fully occupied even if there is no driving pressure exceeding the point value. Stronger. The presence of these ions in the pores of the hydrophilic material allows them to pass through the pores It will have the ability to pass ionic current without the need for fluid spraying. as a result, The pore size can be reduced more easily for hydrophilic materials, and Increase the value of the bubble point without adversely affecting the current carrying capacity by ions, and spray the liquid. Can be minimized. In addition, the relationship between porosity and resistance is less than hydrophobic for hydrophilic materials. It is more direct than in the case of sexual materials. Some forms of nylon (e.g., nylon 6 and nylon 6/6) have a porous electrode This is an example of a hydrophilic material having a high water absorption suitable for use as a base material. Example below In the example of nylon identified in -3, at a relative humidity of 65% and a temperature of 20 ° C. It has a water absorption of 4.0% to 4.2%. Nevertheless, traditional medical grades such as PET and PeBax The material is hydrophobic. Ions in the medium are likely to occupy the pores of the hydrophobic membrane In addition, there is no driving pressure exceeding the value of the bubble point of the material as compared with the hydrophilic material. result Typically, hydrophobic materials require more liquid flow through the pores to bring ions into the pores. To transfer electrical energy across porous materials. I can get it. For such materials, the inflation pressure of the body Should be above the bubble point to allow efficient ion transport. In addition, the higher surface tension of hydrophobic materials trying to restrict ion flow into the pores The hydrophobic material also causes material breakage in the pores compared to the hydrophilic material It shows a bigger trend. Large potential across each pore in hydrophobic materials The difference is the separation of water molecules, dielectric breakdown of the membrane material, and localized overheating. Would. Failure is related to high temperature effects, opening pores depending on the material and The surrounding material is baked, generally reducing the quality of the material. In addition, material breakage can result in black tissue It produces the same harmful tissue effects as CD resection, such as burning. Therefore, the water absorption characteristics of the porous material are changed from more hydrophobic characteristics to more hydrophilic characteristics. Changes offset unwanted electrical features without changing pore size or porosity can do. For example, material breakage due to high current density or potential drop in the pores Loss incidents are reduced by increasing the porosity of the material. But material damage Incidents such as regenerated cellulose, nylon 6 and nylon, which generally have high water absorption, By selecting a hydrophilic material such as Ron 6/6, it can be reduced without changing the porosity. I can do it. Instead, coatings and surface treatments that make it more hydrophilic Not applicable to materials. For example, some materials have specially formulated hydrophilic coatings. Immersed in a coating and exposed to ultraviolet light to bind the coating to the material surface. ing. If the coating withstands the ablation temperature without degradation, This approach is particularly useful when a "balloon" material is used for the body 22. stand. Cancels other unwanted electrical features that are dependent on pore size, porosity and water absorption characteristics Other measures are taken to do so. For example, for larger pore materials, Or, when a porous hydrophilic material is used, the fluid pressure across the body 22 is controlled. This controls the spray rate. Instead, for larger pore materials or a porous hydrophilic material is used. In some cases, materials that increase viscosity and thereby reduce application rate can be Added to the liquid. Examples of materials added to increase viscosity include ion control Last (radiopaque) material, non-ionic glycerol or concentrated mannini Toll solution is included. For example, the electrical performance of woven materials with larger pore sizes is The addition of an ion-radiation opaque co-trast material, such as Assisted. By adding a radiopaque material to the aqueous solution, the body 22 becomes fluorescent. Seen under light fluoroscopy (ultrasound cardiac fluoroscopy based on Cotrast material). porous The flow resistance of the quality material is effectively increased by the increased viscosity of the medium. The use of an ionic material that increases viscosity allows the resistance of the membrane to be based on the concentration of the ionic material. It is not necessary to raise the resistance excessively. The following Table-1 shows the woven nylon 13.0 mm Results from in vitro experiments using ion-opaque materials by the disk detector are required. About. Table-1 Effect of ion contrast material on ablation with woven nylon disc Note: All damage dimensions are based on the fade characteristics at 60 ° C. Table 1 shows that the ion contrast media achieved comparable resistance results and the desired loss. It shows that the power required to create a wound can be reduced. For porous materials, either hydrophilic or hydrophobic, the system 10 comprises a body Can be equipped with a device to detect impedance close to the interface between tissue and tissue You. As FIG. 9 shows, the impedance is not affected despite the increase in the spreading rate. Until the flow stabilization limit is reached. Reduce. By detecting the impedance, the minimum flow rate R_MIN(There, I And the maximum flow rate R_MAX(More can happen To control the spray flow rate (because of salt or moisture overload conditions) be able to. The surface area of the electrode 30 immersed in the conductive medium in the body is: Increase ion transport To be increased. But, The small shape of the body feature is, Impose practical constraints on electrode dimensions. When the electrode 30 approaches the pores 44 of the main body 22, Ion transport through conductive media Also increase the efficiency of. Also, Structural features that exhibit a flexible, small withered shape this This is a practical constraint for consideration. Formation of the main body 22 The expandable and collapsible body 22 comprises External or internal circumference of glass mold Formed by In this configuration, The external dimensions of the mold are Extensible-can wither It matches the desired expanded configuration of the cutting body 22. The mold is The desired wall thickness is reached It is immersed in the solution of the main body material by a predetermined procedure until it is formed. The mold is Then molding It is etched away, leaving the expanded, deflated body 22 that can be withdrawn. instead of, The expandable and collapsible body 22 comprises Extruded further Blow molded from the tube. In this configuration, The main body 22 Adhesive or hot melt Sealed at one end using a garment. The other end of the main body 22 Remains open ing. The expandable and collapsible body 22 comprises Installed inside the mold. An expansion medium such as a high-pressure gas or fluid It is introduced from the open tube end. Chu When the sleeve-shaped body 22 is expanded to take a mold shape, it is exposed to heat. Molded The expandable and retractable body 22 comprises It is then withdrawn from the mold. The porosity of the main body 22 is CO2 laser, Excimer laser, YAG laser, Takaide Force YAG laser, Either before or after molding by electron grain bombardment, etc. available. As explained earlier, To improve the electrical characteristics of the body 22 for tissue resection In order to further enhance the hydrophilicity of the surface, Coatings and surface treatments are also applied. A commercially available porous material is also molded into the body 22. Regenerated cellulose For such materials with poor adhesion formed by chemical processes such as The material is Immersion processing (schematically shown in FIG. 32A, I will explain later), By injection molding , Or, by changing the diameter and outer shape during extrusion molding, it becomes chemically three-dimensional shape Molded. Thermal bonding and laser welding, Those materials to be joined by ultrasonic welding and adhesive For To form a three-dimensional shape from the sheet in which the material is used , There are various ways to use these bonding and welding techniques. Fixtures and mandrels Is It is used to shape the body 22 in relation to heat and pressure. 19 to 23 A desired three-dimensional shape of the body 22 for cutting the porous material 200 It shows a preferred method for molding into a. As shown in FIG. Sheet 200 Is installed in the molding cavity 202 on the fixture 204. The shape of the molding cavity 202 is It corresponds to the shape desired for the distal end of the body 22. In the illustrated embodiment, Its shape is almost hemispherical. As FIG. 20 shows, Forming mandrel 206 forms a portion 208 of sheet 200 Push into the molding cavity 202. The shape of the molding mandrel 206 is Mold cavity 202 Matches the hemispherical shape of The mandrel 206 Sandwich the material part 208 While fitting, it fits in the cavity 202 securely. Now the desired hemispherical shape is obtained by the pressure Is set on the material portion 208. Either molding mandrel 206 or molding cavity 202 Or Or both are heated, Added to the material part 208 in the molding cavity 202 Heat set can be given. Pressure in the molding cavity 202; Opsi The heat in The material portion 208 is formed from a flat shape into a desired hemispherical shape ( See FIG. 21). The sheet with the previously molded portion 208 Removed from the fixture 204, It is mounted on a finishing fixture 210 (see FIG. 22). Finishing fixture 210 Is A distal end 212 having a shape that matches the shape of the previously molded portion 208 Have. Part 208 is Fits on the distal fixture end 212. The finishing fixture 210 is Although it is hemispherical in the illustrated embodiment, Body 22 Has a proximal end 214 having the desired shape. Sheet 200 is The pleats are well formed around the proximal end 214 of the fixture 210. I have arrived. The finishing fixture 210 is Surrounding material of seat 200 is overlaid It has a base region 216 that is gathered with pleated 218. Sheet 20 0 is This will ensure that the entire shape of the fixture 210 is followed. The finishing fixture 210 is Attached to sheet 200 of desired shape of body 22 Heated to help give a proper heat set. To facilitate molding The clamshell mold (not shown) Further fixed around the fixture 210 Is done. Now, the sheet material formed as the porous body 22 (see FIG. 23) Fixture Glide off 210. Collected around the base region 216 of the fixture 210 The pleats 218 of the material Glued together, for example by heat bonding or ultrasonic welding It is. with this, Forming a neck portion 220 of reduced diameter on the body 22; Catheter catheter Facilitates attachment of body 22 to the end of the tube. Before pleating, The sheet end 217 is Elements that come together during pleating It is cut into parts to minimize material volume. After pleating, excess Material is It is folded back and glued to the neck part 220, And / or Must be If Cut to form a smooth transition between neck 220 and distal end 208 Taken. instead of, After removing from the fixture 204, The previously molded part 208 The provided sheet 200 is Hanging around an expandable fixture 222 (see FIG. 24) Handed over. The proximal end 217 of the seat 200 Installation by fastening member 223 The object 222 is tightly fastened around the neck portion. The fixture 222 is Expand using gas or liquid to the shape required for body 22 Balloon (for example, (Made of Teflon material). So Thereby, the sheet 200 is For a fixture 222 that expands to take the desired shape Therefore, it is molded. Before or during expansion of the fixture 222, Heat is applied to the edge 217 of the sheet 200 And Softens the material and assists in forming. External pressure also at the proximal end of seat 200 Department, Assists in creating neck portion 220 with the desired reduced diameter. This What In addition, the proximal end 217 helps to prevent the material from "bunching". The fixture 222 itself is Gases and liquids heated to further expand the fixture Is heated by using Heat is The sheet 20 has a desired shape of the main body 22. 0 is additionally heat set. The outer clamshell mold (not shown) Affixed around fixture 222 to facilitate molding. instead of, Food The outer shell made of glass or other material that is removed by engraving, To give the desired final shape Used for Used to mold body 22 using either fixture 204 or 222 Even for misalignment heating processing, To prevent the pore size from changing significantly during heat processing, Heat sink (not shown) The previously molded end portion 208 was cooled. Used for instead of, The effect of heating on pore size is In the first example before molding into the body 22 Supposed at the time of forming the sheet 200, Be considered. For example, If the pores are molded If it opens inside, The pores should be compared during manufacture to account for dimensional increase during molding. It is illustratively formed smaller. Thus, The desired pore size is Sheet 22 This is ultimately achieved during molding. After molding The fixture 222 is contracted, Pulled out (see Figure 25) . The molded body 222 remains. Yet another alternative (see FIGS. 26 and 27) is: The main body 22 Two By joining the preformed part 225 along the surrounding seam 224 Formed. In the illustrated embodiment, Part 225 is Surplus material around the periphery Resect, It is shaped as a hemisphere as shown in FIGS. Part 225 Is Based on the characteristics of the material, In the same way, it is preformed by molding Become. The seam 224 joining the two parts 225 Thermal bonding, based on the nature of the material Ultrasonic welding, Laser welding, Adhesive bonding, It is formed by sewing or the like. Adopted The method of bonding and suturing The seam is selected to ensure that the seam forms an airtight and liquid tight part It is. The tensile strength of the seam 224, Should exceed the foaming point value of the porous material is there. instead of, Two substantially circular shaped pieces of porous material cut from sheet into predetermined dimensions The flat part is Joined around their perimeter by seams without preforming . with this, Creates a normally wilted disk surrounding an open interior. In use , By introducing air or liquid into the open interior, Disk is required for body 22 The shape is expanded. Discs, Internal support structure to shape the disc to the desired shape Construction Surrounds the body 54 (schematically illustrated in FIGS. 5 to 7). Preferably, After joining the hemispherical or flat portions 225 with seams 224, Shi Excess material that has spread beyond the beam 224 is cut off. still, Organization and seams Contact with the slightly roughened surface of 224 may cause trauma, Combined part Minute 225 is Preferably it is turned over. Inside out, Seam 224 (FIG. 28B (As shown) inside the body 22; From direct contact with the organization keep away. As FIG. 28A shows, The joined part 225 is Small hole 2 at one end 252 Open 50, Insert pull wire 254, Attach it to the other end 256, The other end 256 is turned over by pulling it through its hole 250. This So, The attached hemispherical portion 225 will be turned inside out. In the above embodiment, The surrounding seam 224 It extends around the axis of the body 22. instead of, Seam 226 (as FIGS. 29A and 29B show) Body 22 Extends along the axis of Any two preformed into a flat or three-dimensional shape The above portion 228 can be connected to the main body 22. Each has a body part 228 A supporting mating fixture (not shown) is used, Heat and ultrasonic energy Section 228 is kept stationary while is added to create seam 226. As FIG. 30 shows, The other axially extending seams 230 also Sheet Instead of joining to another sheet, Rather porous to partition the sheet It is provided in the material sheet. Furthermore, For more information about partitioned porous electrodes Will be described later. For illustration purposes, FIG. Seam 226, Section along 230 The hemispherical protrusion of the part is shown somewhat exaggerated. Preferably, The resulting body 22 is turned over as just described, Axial direction A seam 226 or 230 extending toward the inside is provided inside the main body 22. The part 225 or 228 shown in FIGS. Flat or 3D shape Regardless of whether it is molded in advance, It doesn't have to be made from the same material And should be aware. Materials with different porous characteristics Seam just as described Joined by instead of, The porous material is Conductive or electrically insulating It is joined by a seam to a non-porous material. As a further alternative, Conductive The material is Bonded to the insulating material by seams, One (conductive) contacts the tissue, Provide an electrode body having dual sides (electrically insulating) that are exposed to the blood pool Can be in fact, Any flexible material suitable for use in connection with the electrode body Combined using seams according to this aspect of Ming. Furthermore, Form the composite electrode body It should also be understood that the number of parts joined together by seams can vary is there. Of course, Various specific shapes are also selected. The preferred shape is Figure 2 shows basically As shown in the figure, the distal end has a spherical shape with a spherical contour and is symmetric. However , Asymmetric or non-spherical shapes are also used. For example, Extensible-can wither The main body 22 that can be Curved inward to attach the catheter tube 12 Or Formed with a flat end profile that creates a neck. As explained later, FIG. 33 and An elongated cylindrical shape is also used, as shown at 34B. FIG. An alternative expandable and collapsible porous body 50 is shown. In this example, The body 50 is typically shaped to assume an expanded configuration It consists of an open-pored foam. The electrode 30 Surrounded in foam body 50 Have been. A high osmotic pressure liquid medium 38 fills the open porosity into the foam body 50. Introduced, As described above, the desired ion transport of the ablation energy can be performed. I have to. Ion transport using the foam body 50 also If body 50 controls the spray rate External porosity that gives a porosity smaller than the porosity of the foam body 50 to control If you have a skin 51 (as shown on the right side of FIG. 10), To be executed And becomes. In this configuration, The sliding sheath (as described above) is the catheter tube 12 Is advanced along The foam body 50 is compressed into a deflated form. Similarly, Pull the sheath If you can Remove compression force. The foam body 50 without the sheath is Bounce open Come Expandable-retractable body 50 is returned to its expanded configuration. In the preferred embodiment shown, The distal steering mechanism 52 (see FIG. 1) Deploying However, even after deployment, the operation of the porous electrode structure 20 is enhanced. The control mechanism 52 can be changed You. In the illustrated embodiment (see FIG. 1), The steering mechanism 52 By handle 18 It has a rotating cam wheel 56 connected to the held external control lever 58. rotation The ring 56 The proximal ends of the left and right steering wires 60 are held. The wire 60 Resection Through the catheter tube 12 with the energy signal wire 32, End Chu Resilient flexible wire or leaf spring (not shown) adjacent the probe end 16 Are connected to the left and right sides of the Furthermore, This detail and other types of maneuvers, reference By the time, Lankist and Simpson's U.S. Pat. 5, 254 No. 088. As shown in FIG. The leaf spring of the steering mechanism 52 catheter Supported within distal end 16 of tube 12. As FIG. 1 shows, Control When the bar 58 is moved forward, Pull one steering wire 60 to release the leaf spring Bend or bend, At the same time, the distal catheter end 16 and the electrode structure 20 are connected. Bend or bend in the direction. When the control lever 58 is moved backward, The other steering y The leaf spring 62 is bent or bent by pulling the At the same time, Instead of bending or bending the catheter end 16 and the electrode structure 20 in the other direction, Figure As 32C shows, The steerable leaf spring 268 is End of porous body 22 It is the portion of the end fitting 270 that is attached to the end from itself. This structure In The leaf spring 268 is In the tube 272 inside the porous body 22 Extends beyond the distal catheter end. Attached to leaf spring 268 Steering wire 60, 62, Through tube 272. Leaf spring The proximal end of 268 is Takes a hub 274 attached to the distal catheter end 16 It is attached. In this configuration, By moving the control lever 58 on the handle 18 back and forth, In the body 22 In this case, the leaf spring 268 is curved in both directions. Leaf spring 268 Is Move the end fitting 270, Many in the direction in which the leaf spring 268 curves The hole body 22 is deformed. In either configuration, The steering mechanism 54 Extensible-witherable body In the withered form of It can be used even in its expanded form. FIG. 32A, 32B is Perforated end fitting 270 and leaf spring 268 The preferred method of attachment to the body 22 is shown. In FIG. 32A, The porous body 22 , A solution of regenerated cellulose 278 with an expandable fixture 278 having the desired shape Inside It is formed by dipping in Details of such an expandable fixture 278 can be found at: Already explained in another context, FIG. 25. The porous body 22 already As explained, It should be noted that it can be formed in various other ways. As FIG. 32B shows, The fixtures are Proximal neck portion 280 and distal neck 282 to form a dip-formed porous body 22. After molding the main body 22, , The expandable fixture 276 includes As also shown in FIG. 32B, Withered and pulled Be pulled out. As FIG. 32B shows, The distal neck portion 282 For example, using an adhesive , Or adhesive bonding or thermal bonding, Mechanical joining, screw, Winding, Or any of these With the sleeve 288 attached by the combination Terminal fittings Mounted around 270. The mounting fixture 270 is As already explained, A leaf attached to it in advance A spring 268, Related components. First to the fixture 270 Once attached, The proximal neck portion 280 of the body 22 Leaf spring 268 Oriented in the opposite direction. After attaching the distal neck portion 282 to the fixture 270, The main body 22 FIG. 32C Around the distal fitting 270 to cover the leaf spring 268 as shown by Is turned over. The proximal end of leaf spring 268 Distal catheter end 16 Attached to a hub 274 supported by the Turned proximal neck part 2 80 is A sleeve 286 is then used to attach to the distal catheter end. The sleeve 286 is Adhesive bonding and heat bonding, Mechanical joining, screw, Winding, Or this Take it around the catheter tube in various ways, including any of these combinations. Attached. Various alternatives for attaching the porous electrode body to the end of the catheter are: "tube Trunk element that attaches to an expandable and collapsible structure with wires and wires It is disclosed in a co-pending patent application with the name BS label 2456A-6). As explained in more detail later, The end fitting 270 is On the porous body 22 It can also function as a conductive part without holes. A similar fixture 270 is Same purpose To be located elsewhere on the porous body 22. The tip (not shown) Instead or in combination with leaf spring 268 And is attached to the end fitting 270. From there, The probe is in the body 22 ( Inside) On the handle 18 through the catheter tube 12 It extends to a suitable push-pull controller (not shown). The probe is a catheter Is movable along the axis of the tube 12. On end fitting 270 Is pushed and pulled in the axial direction, Thereby, the main body 22 is extended, Or shorten it. Furthermore, For more information on attaching the end fitting to the electrode body, see "Control at the end Vertical or Operable Expandable-Collapsible Electrode Structure "(Patent Attorney Label 24 58A-4) in a co-pending patent application. 33 and 33A / 33B Combined with the end fitting as shown and As shown in FIGS. 32B and 32C, Attached to the distal catheter end 16 1 illustrates an exemplary elongated cylindrical electrode body. In FIG. The main body 290 To form distal and proximal neck portions 280 and 282 In order to It is formed into an elongated shape by extruding, dipping, or molding by changing the radius. Suitable The appropriate end fitting 270 (shown in phantom) Within the distal neck portion 282 Attached to the The elongated body 22 As shown in FIGS. 32B and 32C To complete the assembly. The proximal neck portion 280 Then shown in FIG. 32C. Attached to the distal catheter end 16 as shown. 34A and 34B, The main body 22 Uniform (as shown in FIG. 34B) The tube 292 of the material formed by extrusion molding, molding or immersion with a large radius It is formed from In this configuration (see FIG. 34B) Was previously disclosed The seam 294 formed like this The end of tube 292 is closed. tube The proximal end of 292 is Around tubular bore 296 for attachment to distal catheter end 16 Sealed. instead of, The end of tube 292 is (The virtual line in FIG. 34B Sealed around the distal fitting 270 (shown). In the latter case, Ju 292 Before attaching to the distal end 16 of the catheter, the distal fitting 270 It is turned over around. The pattern of the pores 44 defining the porous region of the body can be varied. Preferably, Figure As outlined in 2 and 3, Extensible-less of the body 22 that can wither At least the proximal one-third of the surface There is no pore 44. Extensible-retractable at least one-third of the surface of body 22 The reason for not providing the pores 44 on the minute is Desirable for several reasons. This part Through Not in contact with the normal organization, as a result, Even if there is a de facto electrode boundary, what It does not fulfill its purpose. Furthermore, This part also shows the smallest diameter. Also If it is electrically conductive, This part Undesired maximum current density Will have. The proximal portion of the smallest diameter that is not normally in tissue contact By leaving it without Scalable-withering that will make tissue contact The maximum current density is ensured at or near the distal end of the body 22 where To be distributed. The resection is performed with the distal portion of the body 22 oriented so as to make end contact with the tissue. If you expect The porous area is Of course expandable-retractable body 22 Should be pointed around the tip of the distal end. Face to face this end In order to The porous area is As FIGS. 2 and 3 show, From the end 1/3 of the body 22 Consists of a continuous cap that is covered in half. But, End contact with tissue If tactile is intended, In the preferred embodiment (see FIG. 11), The conductive porous region is Separately arranged in a concentric "bull's eye" pattern around the distal tip of body 22 It is partitioned into an energy transfer zone 62. The resection is performed with the side region of the body 22 oriented so as to contact the tissue If so, The porous area is Circumference around the end 1/3 to 1/2 of the body Axially elongated energy transfer zones 62 (see FIG. 12) spaced apart in the direction It is preferably partitioned. When the porous region is composed of partitioned zones 62 on the body 22, Guru inside A sealed cannula 64 (see FIG. 13) that has formed a plurality of liquids 38 each individually. It is used for transporting to the hole area partitioning section 62. Each kibo 64 Individually lumen 66 Is in communication with It receives the conductive liquid of one of the porous compartments 62 that it is in charge of . A number of hearts 64 Furthermore, some, However, it is not all carefree 64 By selectively inflating with the body, More specifically control the shape of the expanded body 22 It also gives you the ability to The mind 64 Molded separately and inserted into the body 22, Or they are The expandable and collapsible body 22 is formed integrally during molding. You. As FIG. 12 shows, The partitioned porous zone 62 is More expandable- It is also well adapted for use in connection with withering of the body 22 which can be withered. In this configuration, Non-porous electrodes are Consisting of pleated or foldable areas 68 ing. To create these regions 68, The type of the main body 22 is Expandable and wither Material can be formed slightly thinner along the desired area 68, With dent Be killed, It has a preformed surface profile to be ribbed. Expansion The stretchable and retractable body 22 comprises Consistently and uniformly lift the body 22 from itself While shrinking in the circumferential direction Wither around these pleated areas 68. Thus , The resulting withered shape is It is more uniform and compact. The retractable body 22 shown in FIG. Used for other patterns in the porous area Should be used. In the fold area 68, More if needed A pore is also provided. FIG. Of the expandable and collapsible electrode structure 70 that performs a dual action. An example is shown. The structure 70 is As described above, the internal electrode 30 is housed therein. It has an expandable and collapsible body 22. The main body 22 Conductive fluid 3 8 Also, as just described, ion transport of electrical energy It also has one or more porous regions 62 to allow. The structure 70 shown in FIG. In addition, one or more conductive It also has a region 72. In one embodiment (as FIG. 14 shows) Without holes The conductive region 72 Spatter rings, Evaporation, Ion beam coating, Deposited Electroplating covering the seed layer, Or expandable by a combination of these processes- Gold coated on the body 22 that can wither, platinum, Platinum / Iridium It is composed of such metals. instead of, The conductive region 72 without holes is On the surface of the body It also consists of a fixed thin foil. Further alternatively, The conductive region 72 without holes is Supported at one or more locations by the porous body 22 (the distal attachment shown in FIG. 32C). It can also consist of a rigid attachment (such as a tool). Signal wires in the main body 22 (Fig. Show Is not) It is electrically connected to the non-porous electrode. The signal wire is hand Catheter tubing to connect to connector 38 held by It passes through 12. In the preferred embodiment (see FIG. 15), The non-perforated conductive area 72 extends through the interior of the body. At the desired point of electrical connection, Insulated signal wire 2 meandering through body 22 6. The electrical insulation at the end of the serpentine wire 26 has been removed. And The portion of the wire that is preferably planarized to serve as conductive region 72 Exposed. In the flattened area, Fixed to main body 22 with conductive adhesive 73 Attached. The adhesive 73 is More preferably, of the body 22 through which the wire 26 passes The area is also painted to seal it. The same signal wire 26 Books many times Meandering through body 22, A number of regions 72 are formed as needed. A non-porous electrode 72; Expandable and collapsible electrodes with associated signal wires For various methods of attaching to the main body 22, "Improved electrical connection of electrode structure Continued "(Patent Attorney Label 2458A-5) is described in a co-pending patent application. . The non-porous electrode 72 Used to detect electrical activity in myocardial tissue. Inspection The electrical activity issued is External controller to process potential for analysis by surgeon Sent. By that processing, Potential or to identify potential arrhythmic lesions A map of the negative event is created. Once identified by the non-porous electrode 72, Porous area 62 Is To deliver radio frequency energy as previously described to remove the lesion Used for instead of, Or in combination with the detection of electrical activity, The non-porous electrode 72 Pace news Used to send a number. in this way, Non-porous electrodes are pace mapped or tuned Can perform mapping. Preferably (see FIG. 16), The surface of the main body 22 For unipolar or bipolar detection An electrode 100 suitable for removing a source is held. These electrodes 100 Body 22 Is located on the inside surface of the Their action for detection and / or pacing Is It is not compromised because of the good conductive characteristics of the body 22. Installation of different electrodes Used for monopolar or bipolar detection or for pacing It is. For example, The paired electrodes having a length of 2-mm and a width of 1-mm are inside the main body 22. It is provided on the side surface. Connecting wires 102 are attached to these electrodes 100 You. To prevent high osmotic pressure solutions from shorting these electrodes, To do that, ( Must be covered with electrical insulation 104 (e.g., epoxy or adhesive). Good Best of all, The distance between the electrodes is about 1 mm, Ensures good bipolar action potential maps I am trying to. Preferred locations for these internal electrodes are: End of structure 22 The tip and the center. Furthermore, If many zones are used, Between the resection areas It is desirable to provide electrodes. Opaque to allow surgeon to guide device to target area under fluoroscopy It is also desirable to provide a special marker 106 on the inside surface of the body 22. For this purpose , Any high atomic weight material is suitable. For example, Platinum or Platinum / Iriuji Is used to make the marker 106. Preferred of these markers 106 The installation location is The tip and center of the distal end of the structure 22. Thereby, Expandable and collapsible structure 7 shown in FIG. 0 is The use of a "solid" non-porous electrode 72 is combined with a "liquid" or porous electrode 62. I'm making it. An expandable and collapsible structure is Treatment using one electrode action Mapping of myocardial tissue for purposes, For therapeutic purposes using different electrode actions First, the myocardial tissue can be excised. In an alternative embodiment, The non-porous electrode 72 of the structure 70 Sending radio frequency energy Used in series with the porous region 62 to ablate tissue. With this configuration Is The signal wire covering the area 72 Is electrically connected to the generator 40; It carries radio frequency energy for transmission by one or more regions 72. simultaneous To The internal electrode 30 Radio frequency energy for transmission by the medium 38 through the porous body Receive energy. Ion transport across porous structure surrounding region 72 By doing Increase the effective surface area of the ablation electrode. In this example, Expandable-Collapsible Structure Shown in FIG. 70 is An electrode 72 having a first effective surface area for detection and mapping. Combines the use of The first effective surface area is A porous structure surrounding the electrode 72 An ablation to ablate by ion transport of a hyperosmotic liquid across the structure It is selectively increased for the purpose. If liquid spraying is done through the pores, The internal electrode 30 Effective of those areas There is no requirement to increase the electrode surface area. Those areas are radio frequencies The liquid dispersion of the ionic medium through the pores, which takes place when transferring energy, It By itself, it is sufficient to increase the effective transmission surface area of those regions 72. I Scarecrow, If the ion transport takes place with virtually no liquid spray, Radio frequency transmitted The wireless communication using the internal electrode 30 at the same time when the It would also be advantageous to transfer frequency energy. In this example, It should also be noted that regions 72 are themselves made of porous conductive material. It is. in this way, Ion transport is This can be done across region 72 itself. As explained before (see Figure 1), The controller 32 Preferably, Generator 30 Control the transfer of radio frequency ablation energy to the electrodes supported within the body 22 I have. In the preferred embodiment (see FIG. 2), The porous electrode structure 20 includes: To the controller 32 It holds one or more connected temperature sensing elements 104. The temperature detection element 104 Thermistors and thermocouples, Or of that kind It is shaped. The temperature detection element 104 Heat conductive contact with the outside of the electrode structure 20 Touching, During resection, the condition of the tissue outside of the structure 20 is detected. The temperature detected by the temperature detection element 104 is Processed by controller 32 Is managed. Based on the entered temperature, The controller 32 controls the radio frequency by the electrode 30 Adjust the energy transfer time and power level, Desired damage pattern and other resection Achieve the goal. Incorporating the temperature sensing element 104 into an expandable and collapsible electrode body About the different ways `` Improved Electrical Connections for Electrode Structures '' (Patent Attorney This is described in a co-pending patent application entitled Bell 2458A-5). FIG. 31A, As shown in 31B and 31C, The temperature detection element 104 Further Sheet 260, Or near a seam 258 that couples 262 together to the body 22 It is placed inside it. Regarding the formation of such a seam 258, Already explained Thank you 26 to 30. As shown in FIGS. 31A and 31B, Each temperature detection element 104 one Installed on one of the sheets 260, Then it is covered by the other sheet 262. Two sheets 260, 262 is Then they are joined together to form the body 22. Shi Room 258 Surrounds the sensing element. Signal of each detection element 104 Wire 264 is As FIGS. 31A and 31B show, Sheet 260, 262 Extends outside the seam 258 without the seam 258. As explained earlier, The body 22 is preferably turned over (see FIG. 28A). Figure As 31C shows, Both the seam 258 and the enclosed signal wire 264 inside out Is provided inside the main body 22. The signal wire 264 is Connects to controller 32 Threaded through the neck portion 266 to continue. Instead of or in addition to the temperature sensing element 104, Pace electrodes and detection Electrode for As shown in FIGS. 31A to 31C, The inverted electrode body 2 A second seam 258 can also be enclosed. In such a configuration, After turning over , In a seam close to the surface of the material where the intended contact between the body material and the tissue takes place It is preferable to position the electrodes so that they are arranged at the same time. Furthermore, Many ablation energies controlled using many temperature sensing elements For more information on using transmitters, Filed on August 8, 1994, and System and Method for Controlling Tissue Ablation Using Degree Sensing Elements " Pending U.S. Patent Application Serial No. 08/286. No. 930. Example-1 In vitro analysis Three electrode configurations were analyzed: (1) The molecular weight cutoff is 12, 000-14, 000 daltons and within Using a 9% aqueous salt solution as the liquid medium (produced by Spectra) 13mm disc-shaped book composed of dialysis tubing made from regenerated cellulose A porous expandable and collapsible electrode structure according to the invention having a body. (2) a disk of sputtered platinum with a diameter of 13 mm An electrode body, (3) Expandable and witherable half made of aluminum foil with a diameter of 10 mm. It is a spherical electrode structure. In areas where high temperature conditions existed, 0 in animal (sheep) tissue. 5mm Thermistor is embedded. For electrodes (1) and (2), the maximum temperature is This occurred at the edge of the disk-shaped body due to the heating effect. For electrode (3) The highest temperature occurred at the tip of the end of the hemispherical body with the highest current density. Radio frequency electromagnetic power can be used to increase the thermistor temperature to 60 ° C, 70 ° C, 80 ° C or 9 ° C. Adjusted to maintain 0 ° C. The diameter of all lesions marks tissue decolorization It was measured based on a 60 ° C. isotherm. Table 2 below lists the results observed in the in vitro analysis. Table-2 Note: TM indicates that the damage was transmural and the depth was actually greater than Are shown. The perforated electrode structure (1) is compared to a regular metal ablation electrode such as the electrode (2). Convection cooling had minimal effect. This is during certain damage Changing the fluid flow rate and maintaining the thermistor temperature with respect to the porous electrode structure Observed that there was no need to change the power at all. Table 2 shows that when the power is adjusted based on the tissue temperature, the porous electrode structure Showing that it created damage at least as large as the metal-coated electrode structure are doing. The perforated electrode structure is more expensive than metal-coated electrode structures. Had a reasonable impedance level. In this example, a porous electrode structure is used to ablate an epicardial, endocardial, or intra-wall matrix. To be able to create lesions deeper than 1.0 cm under controlled conditions are doing. The dialysis tubing forming the porous electrode structure has high water absorption characteristics. Dialysis The tube becomes much more flexible when exposed to water. The molecular weight cutoff is 1 2,000 to 14,000 daltons. Larger or smaller molecules Volume cutoffs are available from Spectrum. Dialysis test Conversion of molecular weight cut-off to predicted pore size for tubes is described in “Dialysis / Ultrafiltration. 100, as obtained from the medical instrument booklet 94/95 (p10) 000 daltons is equal to 0.01 μm, 50,000 daltons is 0.004 μm 10,000 daltons equals 0.0025 μm, equals 5,000 dollars. Luton is equal to 0.0015 μm. Dialysis tubing has hydrophilic characteristics and high porosity despite small pore size are doing. As a result, the value of the bubble point is very high and the resistance is Low enough that no liquid flow is required during the supply of energy. Example-2 Finite element analysis A three-dimensional finite element model has a total length of 28.4 mm, a diameter of 6.4 mm, and a diameter of 0.2 mm. Created for a porous electrode structure having an elongated shape with a body wall thickness of 1 mm. 0. A 2 mm diameter metal wire was used as an internal electrode connected to a source of RF energy. It was extended internally along the length of the body to work. The body is 5.0Ω · c A 9% hyperosmotic solution with an electrical resistance of m was filled. The porous body of the structure is Made as an electric wire. Good contact with the heart tissue is in the plane below the electrodes Secured along the entire length of the lying electrode body. Blood contact is on the electrode It was secured over the entire length of the electrode body lying in the horizontal plane. Blood area and tissue area The zones had a resistance of 150 and 500 Ω · cm, respectively. With respect to the electrode body, based on the resistance of 1.2 k-Ω · cm and 12 k-Ω · cm An analysis was performed. Table 3 shows that the RF ablation power was different at different power levels for the porous body of the electrode, The depth of the highest tissue temperature when applied to the porous electrode at various resistance levels is shown. Table-3 FIG. 17 shows that when the porous body has a resistance of 1.2 k-Ω Figure 4 shows the temperature profile when power is applied at 8 watts for 240 seconds. Figure The depth of the 50 ° C. isotherm at 17 is 1.4 cm. FIG. 18 shows that when the porous body has a resistance of 12 k-Ω Figure 4 shows the temperature profile when power is applied for 240 seconds in watts. FIG. The depth of the 50 ° C. isotherm at 8 is 1.0 cm. In all cases, the highest temperature is between the tissue and the edges of the elongated porous structure. Located on the surface. This is the temperature sensing element for the elongated shape of the porous body Is a preferred location at each end edge of the body. Preferably, each edge has at least Should have one temperature sensing element, and many temperature sensing elements Are diagonally opposite sides to ensure that at least one of them faces the tissue Should be placed in The data further shows that the hottest areas, as observed with metal surface electrodes, It does not move too deeply. The hottest areas are for direct detection Consistently at the mid-surface of the tissue-electrode body. Somewhat bigger difference, instrument As encountered in certain other aspects, this feature is characterized by the detected temperature and To reduce the difference between the virtually highest tissue temperature to 0 ° C theoretically if possible Become. A porous electrode body with a higher resistance body (see FIG. 18) When compared to a porous body having a lower resistance (see FIG. 17), A uniform temperature profile was generated. Tissue-electrode by increasing the resistance of the electrode body The same maximum temperature is reached by the additional heat generated at the mid-plane of the body. Required less power. The result is a shallower damage depth Was that. As described previously, by selecting the resistance of body 22, the surgeon can It can greatly affect the damage shape. Use body 22 with small resistance This results in deeper damage, and vice versa. The following table -4 explains the relationship between body resistance and damage depth based on empirical data. ing. Table-4 Compared to non-porous metal surface electrodes due to the reduced thermal conductivity of the porous electrode structure Lesion formation is predicted to be less sensitive to dynamic blood flow conditions around the electrodes It is. Delivery of ablation energy through a porous electrode requires particularly shallow atrial injury. More precise control to obtain the desired damage characteristics. The following Table 5 is based on empirical data and indicates that changes in blood flow This proves that the sensitivity of the porous electrode structure is reduced under the convection cooling condition. Table-5 The use of a porous electrode structure offers structural advantages. It's gold The metal conductive shell is expandable-it can be placed on the outside of the It is to isolate problems of adhesion that can occur as a series of events. The porous electrode structure also avoids potential problems with tissue adhesion to external conductive material Willing to. In addition to these structural advantages, the temperature control of the cutting operation is improved. Cut tissue When using conventional metal electrodes to remove blood, the tissue-electrode interface is Cooled convectively by the flow. Due to these convective cooling effects, the highest tissue temperature The degree region is located deeper in the tissue. As a result, the metal electrode element The temperature condition detected by the detection element associated with Is not directly reflected. In this situation, the condition of the highest tissue temperature is Must be inferred and predicted from the temperature issued. Porous electrode structure 20 or Uses 70 to convectively cool the tissue-electrode interface by the surrounding blood flow To a minimum. Consequently, the region with the highest temperature is located between the tissue and the porous electrode. It will be located in the middle. As a result, the detection element associated with the perforated electrode element The temperature conditions detected by the instrument more accurately reflect the actual highest tissue temperature Will do. Example-3 In vitro experiments show that porous material (Hphi) versus hydrophobic material (Hphb) A comparison was made on items using them as the weave cutting elements. Table- Figure 6 summarizes the results. Table-6 Summary of porous resection material Note: "Material damage" is the presence of material damage as described above. Table 6 shows that the pore size was reduced using a hydrophilic material, Minimize or stop liquid spray through the material, while still allowing Prove that you have to be able to transport on. The hydrophobic porous material enables a high resistance porous electrode to be realized. On the other hand, parent The aqueous porous material enables a low resistance porous electrode to be realized. Get the desired damage characteristics As the above table demonstrates, the same expandable and collapsible porous electrode structure The structure 20 can selectively form either wide and shallow or large and deep damage. . Various methodologies have been used to control the supply of radio frequency energy to achieve this result. Used for A. D50C action In one exemplary embodiment, the controller 2 is (i) from the surgeon. Tissue-electrode where desired damage is to the depth of the boundary between viable and non-viable tissue And / or (ii) the tissue-electrode midplane and boundary Receive the desired treatment result in terms of the highest tissue temperature generated within the lesion during the depth The controller 42 has an input unit 300 (see FIG. 1) for extracting. The controller 42 also provides information on damage boundary depth, ablation power level, ablation time, actual surface Holds a function that correlates the observed relationship between underlying tissue temperature and electrode temperature Processing element 302 (see FIG. 1). Processing element 302 Compares the desired treatment result with the function and selects operating conditions based on the comparison. To achieve the desired treatment result without exceeding the actual or predicted subsurface tissue temperature described above. To achieve. The operating condition selected by the processing element 302 is the control of the ablation power level. Limits the ablation time to the selected target ablation time, Limiting the ablation power level and / or the desired percentage between region 44 and tissue Various aspects of the cutting process, such as the orientation of the porous region 44 of the body 22 including the prediction of the contact of the Can be controlled. The processing element 302 is configured to detect the actual maximum tissue temperature. Expandable and retractable into the weave-held by structure 20 that can collapse Or else it relies on a temperature sensor associated with it. Instead, processing element The client 302 can predict a maximum tissue temperature based on operating conditions. In a preferred exemplary embodiment, the electrode structure 20 is adapted to provide the instantaneous local temperature of the hot mass in the region 44. The temperature (T1) is detected. At least one temperature detecting element 10 is held. Some Temperature T1 at different times is a function of the power supplied to electrode 30 by generator 40. Is a number. The characteristic of the damage is the expression of the depth below the tissue surface in the 50 ° C isothermal area called D50C. Is expressed. The depth D50C depends on the physical characteristics of the porous region 44 (ie its electrical and thermal properties). Conductivity and resistance and dimensions); percentage of contact between tissue and porous region 44; And the local temperature T1 of the hot mass of the RF mass transmitted by the internal electrode 30 ( P); as a function of the time (t) that the tissue is exposed to RF power. For the desired damage depth D50C, further consideration of safety Constraining the selection of the optimal operating conditions among the listed operating conditions You. The principle safety constraints are the maximum tissue temperature TMAX and the maximum power level PM AX. The maximum tissue temperature condition, TMAX, is high enough to cause deep and widespread damage (1 (Generally between about 85 ° C and 95 ° C) However, for safety, it is less than about 100 ° C. It is within the temperature range known to cause fine rupture. TM AX is generated at some distance below the electrode-tissue interface between the interface and D50C. Is recognized. The maximum power level PMAX depends on the physical characteristics of the internal electrode 30 and the power of the RF generator 40. The power capacity is taken into account. These relationships, as illustrated in the above example, are controlled real and simulated realities. Observed empirically and / or by computer models under the conditions tested You. The D50C effect on a certain porous region 44 is restored to the matrix of the above values. All or some of the expressions, empirical data and / or compilations It is expressed by their relational expressions derived from computer modeling. The processing element 302 is capable of handling t = 120 seconds and TMAX = 95 ° C. as described above. This matrix also defines the D50C temperature boundary function for a series of other operating conditions The operating conditions of the box are stored in the memory. The surgeon may further identify features of the structure 20 using the identification codes described above, RF power level PMAX; desired time t; desired maximum tissue temperature TMA The input unit 300 is also used to set X. Based on these inputs, processing element 302 retrieves the desired treatment result. Compare with the function defined in the box. The generator 42 controls the variables of the function Operating conditions are selected to achieve the desired therapeutic result without exceeding TMAX. So, this configuration allows the surgeon to specify the desired To be damaged. In addition, the details that elicit the D50C effect and its use to obtain the desired damage pattern Is referred to herein as `` desired damage characteristics during resection of body tissue. US Patent Application No .: US Patent Application Ser. No. 08 / 431,790. B. Sectioned area: Duty cycle control Various RF energy control methods are shown in FIG. 11 (bulls spaced in the axial direction of the zone). Area shown in FIG. 12) and FIG. 12 (zones circumferentially separated). Used in conjunction with the provided porous pattern. For illustrative purposes, (also called electrode area) 44 is denoted by E (J), where J is a certain zone 44 (J = 1 or not). N) are displayed. As explained previously, each electrode area E (J) represents a zone 44 where J is a certain zone 44 and K represents the number of temperature detection elements on each zone (K = 1 to M) S (J , K) at least one temperature detecting element 104. In this mode, RF power is supplied by a large number of pulses with a duty cycle of 1 / N. The condition is set via an appropriate power switching intermediate plane as described above. The amount of power (P) delivered to each individual electrode area E (J) with a pulsed power supply_{E (J)} ) Is expressed as follows. P_{E (J)}αAMP_{E (J)} ^Two× DUTYCYCLE_{E (J)} In that case: AMP_{E (J)}Is the amplitude of the RF voltage sent to the electrode region E (J), DUTYCYCLE_{E (J)}Is the duty cycle of the pulse expressed as Is a kuru: DUTYCYCLE_{E (J)}= TON_{E (J)}/ (TON_{E (J)}+ TOFF_{E (J)}) In that case: TON_{E (J)}Indicates that the electrode region E (J) emits energy during each pulse period Time TOFF_{E (J)}Indicates that during each pulse period, the electrode region E (J) emits energy There is no time. Expression (TON_{E (J)}+ TOFF_{E (J)}) Indicates a pulse period for each electrode region E (J). Is represented. In this mode, generator 40 provides a 1 / N duty cycle for each electrode area. (DUTYCYCLE_{E (J)}) Can be generated intensively The generator 40 determines that the end of the duty cycle of the previous pulse is equal to the duty cycle of the next pulse. Power pulses for adjacent electrode areas so that they overlap slightly at the beginning of the power cycle Occur in order. This overlap in the duty cycle of the pulse The disconnection period is not caused by the release circuit during pulse switching between successive electrode areas. This ensures that the generator 40 can continuously supply power. In this mode, the temperature controller 42 controls each electrode region (AMP)._{E (J)}) Of the RF voltage Make individual adjustments to the amplitude, which are controlled by generator 40 Power P of the ablation energy transmitted to each electrode area during the cycle_{E (J)}Switch individually You. In this mode, the generator 40 cycles between successive data acquisition sampling periods. I do. During each sampling period, the generator 40 controls the individual sensors S (J, K) Detected by the detection element 104 as output by the controller 42. The selected temperature code TEMP (J) (the highest one of S (J, K)). When more than one sensing element 104 is associated with an electrode area (e.g., If a sensing element located at the edge is used), the controller 42 Register all the detected temperatures for the area, and select TEMP (J) from these. Select the highest detection temperature to configure. In this mode, the generator 40 will locally control each electrode E (J) during each data acquisition period. The detected temperature TEMP (J) to the set point temperature TE established by the surgeon. Compare with MPSET. Based on this comparison, the generator 40 has DUTYCYCLE for other electrode areas_{E (J)}While maintaining the electrode area Amplitude AMP of RF voltage supplied to E (J)_{E (J)}Change the set point temperature TEMP_SE _T TEMP (J) is generated and maintained. Set point temperature TEMPSET may vary depending on surgeon judgment and empirical data. You. A typical set point temperature TEMP for heart ablation is typically 70 ° C. It appears to be in the range of 40 ° C to 95 ° C. Generator 40 is AMP_{E (J)}Is controlled by a proportional control method, a proportional integral derivation (P (ID) A control method or an ambiguous theoretical control method can be adopted. For example, using the proportional control method, if detected by the first detection element Temperature is TEMP (1)> TEMP_SETIs generated by the generator 30 if Amplitude AMP of the RF voltage applied to the first electrode region E (1)_{E (1)}The low On the other hand, the duty cycle DUTYCY for the first electrode region E (1) is reduced. CLE_{E (1)}Keep the same. If the second detection element TEMP (2) TEMP (2) <TEMP_SETIf so, control the generator 30 The control signal is the amplitude AMP of the pulse applied to the second electrode region E (2)._{E (2)}Increase On the other hand, the duty cycle DUTYCYCL for the second electrode region E (2) E_{E (2)}Duty cycle DUTYCYCLE_{E (1)}And maintain the same. If the temperature detected by a certain sensing element is the set point temperature TEMP_SETIn If so, no change occurs in the amplitude of the RF voltage for the associated electrode area. The generator 40 continuously processes the voltage difference input during successive data acquisition periods to AMP in electrode area E (J)_{E (J)}Individually, but on the other hand collective The tee cycle is maintained the same for all electrode regions E (J). like this In addition, the mode maintains the desired uniform state of temperature over the length of the ablation element. I have Using a proportional-integral-derivative (PID) control technology, the generator Changes that occurred during the previous sampling period, as well as The rate at which these changes change over time is also taken into account. Thus, P Using ID control technology, the difference is larger or smaller compared to the previous instantaneous difference. Percentage that the difference has changed, based on whether it has gone down and since the previous sampling period The generator is based on whether it is larger or smaller, MP (J) and TEMP_SETDifferently from a proportionally large instantaneous difference between Respond. Furthermore, the amplitude / collective of the individual electrode areas defined based on the temperature detection The details of controlling the duty cycle are incorporated here by reference. System and method for controlling tissue ablation using multiple temperature sensing elements No. 08 / 439,8, filed May 12, 1995. It can be seen in No. 24. C. Sectioned area: disabling with differential temperature In this control mode, the controller 42 switches to the end of each data acquisition phase at that phase. Best for (TEMP_SMAX) And select the detected temperature. Controller 4 2 is the minimum (TEMP_SMIN) And the detected temperature And select. The generator sets the selected highest detected temperature TEMP_SMAXHigh set point selected Temperature TEMP_HISETCompare with In the comparison, proportional, PID or fuzzy theoretical systems Using a control method to centrally adjust the amplitude of the RF voltage for all electrode areas Generate control signals. In the proportional control plan: (I) If TEMP_SMAX> TEMP_HISETThe control signal is The amplitude of the RF voltage delivered to the area is reduced intensively. (Ii) If TEMP_SMAX<TEMP_HISETThe control signal is Intensively increase the amplitude of the RF voltage delivered to the region. (Iii) If TEMP_SMAX= TEMP_HISETIf it is sent to all areas There is no change in the amplitude of the RF voltage. The generator uses the detected temperature TEMP for amplitude control purposes._SMAX, TEMP_SMINOr between You can select one of the degrees to compare this temperature condition with a preselected temperature condition. You should be aware that The generator has a certain local temperature TEMP (J) and TEMP (J)._SMINArea based on the difference between Control the power supply to the With this execution, the local detected temperature TEMP (J) and TEMP_SMIN Calculate the difference between them and compare this difference with the selected set point temperature difference ΔTEMPSET. You. Therefore, a control signal for controlling power supply to the electrode region is generated. If the local temperature TEMP (J) for a certain electrode area E (J) is ΔTEMP_SE _T The same as or (ie, if TEMP (J) -TEMP_SMIN≧ ΔTEMP_SETso If any) ΔTEMP_SETGreater minimum detected temperature TEMP_SMINIf you pass , The generator The power supply to a certain predetermined area E (J) is cut off. TEMP (J) -TEMP_SM _IN <ΔTEMP_SET, The generator supplies power to that given area E (J). Is restored. Instead, TEMP (J) and TEMP_SMINInstead of comparing EMP_SMAXAnd TEMP_SMINCan be compared. TEMP_SMAXAnd TEMP_SM _IN Is the predetermined amount ΔTEMP_SETIf equal to or exceeds the generator Is TEMP_SMINBlocks all areas except the area where exists. TEMP_SMAX And TEMP_SMINTemperature difference between ΔTEMP_SETIf less, the generator 30 restores these areas. Further details on using differential temperature disabling are incorporated herein by reference. An embedded system that uses multiple temperature sensing elements to control tissue ablation No. 08/1994, filed Aug. 8, 1994. 286,930. D. PID control Regarding the porous electrode structure, the minimum effect of convective cooling by the blood pool is The actual detected temperature condition as the maximum tissue temperature TMAX instead of the assumed temperature To Make it available. As a result, such a structure can also derive its own proportional integral. Outgoing (PID) control technology is used. Available in connection with these electrode structures The illustrated PID control technique uses a time-varying set point temperature curve for monitoring and control. Application for filed June 27, 1994 under the name of "Tissue Heating and Excision Systems and Methods" It is disclosed in pending US patent application Ser. No. 08 / 266,023. Finally, an internal electrode located inside the porous, expandable and collapsible body It should be noted that 30 can be used for mapping myocardial tissue in the heart. is there. In this use, the inner electrode is a core that can take the form of, for example, a potential or a resistance. Detects electrical activity inside the gut. The detected electrical activity is Sent to an external controller that processes the detected activity being analyzed. Furthermore, an internal electrode 3 arranged inside a porous, expandable and collapsible body 0 is alternately used to send a pacing signal or combined with electrical activity detection It should be noted that they can be used together. Thus, the internal electrode 30 Pace mapping or tuning mapping can be performed. Various features of the invention are set forth in the following claims.

───────────────────────────────────────────────────── フロントページの続き (31)優先権主張番号６０／０１０，３５４ (32)優先日平成８年１月19日(1996．1．19) (33)優先権主張国米国（ＵＳ） (31)優先権主張番号０８／６３１，５７７ (32)優先日平成11年４月12日(1999．4．12) (33)優先権主張国米国（ＵＳ） (31)優先権主張番号０８／６３４，３３４ (32)優先日平成８年４月12日(1996．4．12) (33)優先権主張国米国（ＵＳ） (31)優先権主張番号０８／６３１，３５６ (32)優先日平成８年４月12日(1996．4．12) (33)優先権主張国米国（ＵＳ） (31)優先権主張番号０８／６３１，５７５ (32)優先日平成８年４月12日(1996．4．12) (33)優先権主張国米国（ＵＳ） (31)優先権主張番号０８／６３４，３３８ (32)優先日平成８年４月12日(1996．4．12) (33)優先権主張国米国（ＵＳ） (31)優先権主張番号０８／６３１，０７４ (32)優先日平成８年４月12日(1996．4．12) (33)優先権主張国米国（ＵＳ） (31)優先権主張番号０８／６３１，５７３ (32)優先日平成８年４月12日(1996．4．12) (33)優先権主張国米国（ＵＳ） (31)優先権主張番号６３１，２５２ (32)優先日平成８年４月12日(1996．4．12) (33)優先権主張国米国（ＵＳ） (31)優先権主張番号０８／６３４，３３９ (32)優先日平成８年４月12日(1996．4．12) (33)優先権主張国米国（ＵＳ） (31)優先権主張番号０８／６４４，６０５ (32)優先日平成８年４月12日(1996．4．12) (33)優先権主張国米国（ＵＳ） (81)指定国ＥＰ(ＡＴ，ＢＥ，ＣＨ，ＤＥ，ＤＫ，ＥＳ，ＦＩ，ＦＲ，ＧＢ，ＧＲ，ＩＥ，ＩＴ，ＬＵ，ＭＣ，ＮＬ，ＰＴ，ＳＥ)，ＣＡ，ＪＰ (72)発明者パネスク，ドーリンアメリカ合衆国94086カリフォルニア州サニーベイル、ノース・フェア・オークス 382番、アパートメント４ (72)発明者フェイン，ジェイムズ・ジーアメリカ合衆国95070カリフォルニア州サラトガ、ロス・フェリス・ロード17930 番 (72)発明者オーウェンズ，パトリック・エムアメリカ合衆国95014カリフォルニア州クペルティノ、ナンバー４、ノース・ウォールナット・サークル10380番 (72)発明者フレイシュマン，シドニー・ディアメリカ合衆国94025カリフォルニア州メンロ・パーク、ウッドランド・アベニュー855番 (72)発明者トンプソン，ラッセル・ビーアメリカ合衆国94022カリフォルニア州ロス・アルトス、ウェセット・ポートラ・アベニュー 123番 (72)発明者ジャクソン，ジェロームアメリカ合衆国94024カリフォルニア州ロス・アルトス、フォールン・リーフ・レイン 1725番────────────────────────────────────────────────── ─── Continuation of front page (31) Priority claim number 60 / 010,354 (32) Priority date January 19, 1996 (Jan. 19, 1996) (33) Priority country United States (US) (31) Priority claim number 08 / 631,577 (32) Priority date April 12, 1999 (April 12, 1999) (33) Priority country United States (US) (31) Priority claim number 08 / 634,334 (32) Priority Date April 12, 1996 (April 12, 1996) (33) Priority country United States (US) (31) Priority claim number 08 / 631,356 (32) Priority Date April 12, 1996 (April 12, 1996) (33) Priority country United States (US) (31) Priority claim number 08 / 631,575 (32) Priority Date April 12, 1996 (April 12, 1996) (33) Priority country United States (US) (31) Priority claim number 08 / 634,338 (32) Priority Date April 12, 1996 (April 12, 1996) (33) Priority country United States (US) (31) Priority claim number 08 / 631,074 (32) Priority Date April 12, 1996 (April 12, 1996) (33) Priority country United States (US) (31) Priority claim number 08 / 631,573 (32) Priority Date April 12, 1996 (April 12, 1996) (33) Priority country United States (US) (31) Priority claim number 631,252 (32) Priority Date April 12, 1996 (April 12, 1996) (33) Priority country United States (US) (31) Priority claim number 08 / 634,339 (32) Priority Date April 12, 1996 (April 12, 1996) (33) Priority country United States (US) (31) Priority claim number 08 / 644,605 (32) Priority Date April 12, 1996 (April 12, 1996) (33) Priority country United States (US) (81) Designated countries EP (AT, BE, CH, DE, DK, ES, FI, FR, GB, GR, IE, IT, L U, MC, NL, PT, SE), CA, JP (72) Inventor Panesque, Doolin United States 94086 California Sunnyvale, North Fair Oaks 382, apartment 4 (72) Inventor Fein, James G United States 95070 California Saratoga, Los Ferris Road 17930 Turn (72) Inventors Owens, Patrick M United States 95014 California Cupertino, Number 4, North Wo Lunat Circle 10380 (72) Inventor Freishman, Sydney Day United States94025California Menlo Park, Woodland Avenue -855th (72) Inventor Thompson, Russell Bee United States 94022 California Los Altos, Wesset Portra Avenue 123 (72) Inventor Jackson, Jerome United States 94024 California Los Altos, Fallen Reef Re Inn 1725

Claims

[Claims] 1. A wall surrounding the interior area, A lumen capable of transporting the medium to an interior region capable of holding an ion-containing medium, It consists of an element that connects the medium in the internal area with a source of electrical energy, At least some of its walls prevent the passage of macromolecules, while the medium in the inner region Made of a porous material sized to allow the ions contained in Porous material capable of ion transport of electrical energy through the porous material and out of the wall A porous electrode assembly comprising: 2. A wall surrounding an interior region capable of holding the ion-containing medium under pressure; It consists of elements that connect the medium and the source of electrical energy, At least a portion of the wall is substantially free of medium perfusion through the porous material. It consists of a porous material that is formed in a size that can pass ions contained in the body, Porous element capable of ion transport of electrical energy through a porous material and out of the wall A porous electrode assembly made of a material. 3. A wall surrounding an interior region capable of holding the ion-containing medium under pressure; It consists of elements that connect the medium and the source of electrical energy, At least a part of the wall is formed large enough to pass ions contained in the medium. Made of porous material that has passed through the porous material and out of the wall On-transport is possible and the porous material is larger than the pressure in the internal area A porous electrode assembly having a standing point value. 4. A wall surrounding an interior region capable of holding the ion-containing medium under pressure; Consisting of an element that connects the medium to an electrical energy source, At least a part of the wall is formed large enough to pass ions contained in the medium. Made of a hydrophilic porous material that has passed through the porous material and out of the wall Energy transport is possible and the porous material is A porous electrode assembly having a large bubble point value, A porous electrode in which ion transport occurs through the porous material without substantial liquid perfusion. Pole assembly. 5. 5. The porous material according to claim 1, wherein the porous material comprises an ultrafiltration membrane. Electrode assembly. 6. 4. The element as claimed in claim 1, wherein the element comprises a conductive electrode in the interior region of the wall. Or the porous electrode assembly according to 4. 7. 7. The assembly according to claim 6, wherein the conductive electrode comprises a noble metal. 8. A group consisting of gold, platinum, and platinum / iridium as essential components 7. The method according to claim 6, comprising a material selected from the group consisting of: Assembly. 9. The assembly according to claim 1, 2 or 3 or 4, wherein the medium comprises a hypertonic solution. 10. The assembly of claim 9, wherein the hypertonic solution comprises sodium chloride. 11. 11. The assembly of claim 10, wherein the concentration of sodium chloride is at or near saturation. Lee. 12. The concentration of sodium chloride is up to about 9% w / v. Assembly. 13. The assembly of claim 9, wherein the hypertonic solution comprises potassium chloride. 14． 5. The medium according to claim 1, wherein said medium has a resistance of about 150 .OMEGA.cm or less. The described assembly. 15. 5. The medium according to claim 1, wherein the medium has a resistance of about 10 Ω · cm or less. On-board assembly. 16. 5. The method according to claim 1, wherein the medium has a resistance of about 5 .OMEGA.cm. Assembly. 17． 5. The medium according to claim 1, wherein the medium comprises a radiopaque material. Assembly. 18. The electrical resistance of the porous material is at least about 500 ohm-cm. Is the assembly according to 2 or 3 or 4. 19. The electrical resistance of the porous material is about 500 Ω · cm or less. Is the assembly according to 3 or 4. 20. The conductive material is contained in at least a part of the wall. Assembly. 21. 21. The assembly of claim 20, wherein the conductive material of the wall is porous. 22. 21. The assembly of claim 20, wherein the conductive material of the wall is non-porous. 23. 21. The assembly according to claim 20, wherein the conductive material comprises a coating film deposited on a wall. Mumburi. 24. 21. The assembly of claim 20, wherein the conductive material comprises a foil applied on a wall. - 25. 21. The assembly of claim 20, wherein the conductive material is disposed in the wall. 26. Conductive material consists of uninsulated signal wires exposed outside the wall An assembly according to claim 20. 27. 21. The electrode assembly according to claim 20, wherein at least a part of the wall is not made of a conductive material. Lee. 28. 5. The method according to claim 1, wherein at least part of the wall is not made of a conductive material. An electrode assembly as described. 29. In addition, assembled within the interior area to form a support under the wall The electrode assembly according to claim 1, wherein the electrode assembly includes a member. 30. 30. The assembly according to claim 29, wherein the solid support member comprises a metal material. 31. 31. The assembly of claim 30, wherein the metal material comprises nickel titanium. 32. 31. The assembly of claim 30, wherein the metallic material comprises stainless steel. 33. 30. The assembly according to claim 29, wherein the solid support member is made of a plastic material. Lee. 34. Solid support members are assembled and stretched at regular intervals in the circumferential direction. 30. The assembly of claim 29, comprising a splined member. 35. 30. The assembly of claim 29, wherein the solid support member comprises a porous foam. - 36. The wall has a distal zone and a proximal zone, and the porous material is more distal than the proximal zone. The assembly according to claim 1 or 2 or 3 or 4, wherein 37. 37. The acene of claim 36, wherein at least one third of the proximal region is free of porous material. Brie. 38. An assembly as claimed in any one of the preceding claims, wherein the porous material occupies at least 1/3 of the terminal area. Lee. 39. Claims further comprising a radiopaque material carried by the assembly Item 5. The assembly according to item 1 or 2 or 3 or 4. 40. A catheter tube having a distal end; A return electrode; A liquid source of the ion-containing medium; Above catheter tube end, electrically coupled to return electrode through tissue An electrode, a wall having an outer surface surrounding the periphery of the inner region; An electrode consisting of a lumen carrying the ion-containing medium and a conductive element in the interior region When, Means to connect the conductive element to the energy source to transfer energy , At least a portion of the wall impedes the passage of macromolecules while the medium in the interior region Made of a porous material that is large enough to pass ions contained in The porous material heats the tissue between the return electrode and the electrode for transport to the return electrode, By ions of electrical energy from the conductive element through the medium to the outer surface of the wall A living tissue heating device that enables transport. 41. A catheter tube having a distal end; A return electrode; A liquid source of the ion-containing medium; Above catheter tube end, electrically coupled to return electrode through tissue An electrode, a wall having an outer surface surrounding the periphery of the inner region; An electrode consisting of a lumen carrying the ion-containing medium and a conductive element in the interior area When, Means to connect the conductive element to the energy source to transfer energy , At least a part of the wall inhibits the passage of the polymer, while the medium in the internal region It is made of a porous material formed to have a size that allows the contained ions to pass through. Through the media for delivery to the return electrode to ablate tissue between the Ionic transport of electrical energy from the conductive element to the exterior of the wall Biological tissue resection device. 42. A catheter tube having a deployment end in the atrioventricular chamber of the heart; A return electrode; A liquid source of the ion-containing medium; Above catheter tubing end, electrically coupled to return electrode through heart tissue A wall having an outer surface surrounding the perimeter of the inner region; Consisting of a lumen carrying the ion-containing medium to the region and a conductive element in the interior region Electrodes and Means to connect the conductive element to the energy source to transfer energy , At least a portion of the wall impedes the passage of macromolecules while the medium in the interior region Made of a porous material large enough to pass ions contained in The media is transported to the return electrode to ablate the heart tissue between the electrodes. Enables ionic transport of electrical energy from conductive elements through to the exterior surface of the wall Heart tissue resection device. 43. A catheter tube having a distal end; A return electrode; A liquid source of the ion-containing medium; Above catheter tube end, electrically coupled to return electrode through tissue An electrode, a wall having an outer surface surrounding the periphery of the inner region; An electrode consisting of a lumen carrying the ion-containing medium and a conductive element in the interior region When, Means to connect the conductive element to the energy source to transfer energy , At least a portion of the wall substantially eliminates ions contained in the medium in the interior region. The porous material must be large enough to pass through the porous material without liquid perfusion. Transfer to the return electrode to heat the heart tissue between the return electrode and the electrode. Ion transport of electrical energy from the conductive element through the medium to the exterior of the wall A living tissue heating device that enables transport. 44. A catheter tube having a distal end; A return electrode; A liquid source of the ion-containing medium; Above catheter tube end, electrically coupled to return electrode through tissue An electrode, a wall having an outer surface surrounding the periphery of the inner region; An electrode consisting of a lumen carrying the ion-containing medium and a conductive element in the interior region When, Means to connect the conductive element to the energy source to transfer energy , At least a portion of the wall substantially eliminates ions contained in the medium in the interior region. The porous material must be large enough to pass through the porous material without liquid perfusion. To ablate the tissue between the return electrode and the electrode, for delivery to the return electrode, By ions of electrical energy from the conductive element to the exterior of the wall through the medium A biological tissue resection device that enables transport. 45. A catheter tube having a deployment end in the atrioventricular chamber of the heart; A return electrode; A liquid source of the ion-containing medium; Above catheter tubing end, electrically coupled to return electrode through heart tissue A wall having an outer surface surrounding the perimeter of the inner region; Consisting of a lumen carrying the ion-containing medium to the region and a conductive element in the interior region Electrodes and Means to connect the conductive element to the energy source to transfer energy , At least a portion of the wall substantially eliminates ions contained in the medium in the interior region. The porous material must be large enough to pass through the porous material without liquid perfusion. And transfer to the return electrode to ablate the heart tissue between the return electrodes. To the ions of electrical energy from the conductive element to the outside of the wall through the medium A biological tissue excision device that enables transport. 46. A catheter tube having a distal end; A return electrode; A liquid source of the ion-containing medium; Above catheter tube end, electrically coupled to return electrode through tissue An electrode, a wall having an outer surface surrounding the periphery of the inner region; A lumen for carrying the ion-containing medium to the received interior region, and a conductive element in the interior region. Electrodes consisting of Means to connect the conductive element to the energy source to transfer energy , At least a portion of the wall substantially eliminates ions contained in the medium in the interior region. The porous material must be large enough to pass through the porous material without liquid perfusion. To heat the tissue between the return electrode and the electrode, for delivery to the return electrode, Ion transport of electrical energy from the conductive element through the medium to the exterior of the wall Enable the porous material to have a bubble point value greater than the internal pressure. Body tissue heating device. 47. A catheter tube having a distal end; A return electrode; A liquid source of the ion-containing medium; Above catheter tube end, electrically coupled to return electrode through tissue An electrode, a wall having an outer surface surrounding the periphery of the inner region; A lumen for carrying the ion-containing medium to the received interior region, and a conductive element in the interior region. Electrodes consisting of Means to connect the conductive element to the energy source to transfer energy , At least a portion of the wall substantially eliminates ions contained in the medium in the interior region. The porous material must be large enough to pass through the porous material without liquid perfusion. To ablate the tissue between the return electrode and the electrode, for delivery to the return electrode, Ion transport of electrical energy from the conductive element through the medium to the exterior of the wall Enable the porous material to have a bubble point value greater than the internal pressure. Body tissue resection device. 48. A catheter tube having a deployment end in the atrioventricular chamber of the heart; A return electrode; A liquid source of the ion-containing medium; Above catheter tubing end, electrically coupled to return electrode through heart tissue A wall having an outer surface surrounding the periphery of the inner region, and an inner pressure from a liquid source. A lumen for transporting the ion-containing medium to the interior region under force, and a conductive energy in the interior region. An electrode consisting of Means to connect the conductive element to the energy source to transfer energy , At least a portion of the wall substantially eliminates ions contained in the medium in the interior region. The porous material must be large enough to pass through the porous material without liquid perfusion. And transfer to the return electrode to ablate the heart tissue between the return electrodes. To the ions of electrical energy from the conductive element to the outside of the wall through the medium A biological tissue excision device that enables transport. 49. 40. The medium of claim 40 or 41 or 42 or 43 or 44 or 45. The apparatus according to 45 or 46 or 47 or 48. 50. 50. The device of claim 49, wherein the hypertonic solution comprises sodium chloride. 51. 51. The device of claim 50, wherein the concentration of sodium chloride is at or near saturation. 52. 51. The method of claim 50, wherein the concentration of sodium chloride is up to about 9% w / v. apparatus. 53. 50. The device of claim 49, wherein the hypertonic solution comprises potassium chloride. 54. 43. The medium of claim 40 or 41 or 42, wherein the resistance of the medium is about 150 Ωcm or less. The apparatus according to 43 or 44 or 45 or 46 or 47 or 48. 55. The apparatus of claim 54, wherein the medium has a resistance of about 10 ohm-cm or less. 56. The apparatus of claim 54, wherein the medium has a resistance of about 5 ohm-cm. 57. 41. The porous material has an electrical resistance of at least about 500 ohm-cm. Is a device described in 41 or 42 or 43 or 44 or 45 or 46 or 47 or 48. Place. 58. 41. The porous material has an electrical resistance of at least about 500 ohm-cm or less. Or 41 or 42 or 43 or 44 or 45 or 46 or 47 or 48 apparatus. 59. Claim 40 or 41 or 42 or at least a portion of the wall comprises a conductive material. 43. The apparatus according to 43 or 44 or 45 or 46 or 47 or 48. 60. 60. The device of claim 59, wherein the conductive material of the wall is porous. 61. 60. The device of claim 59, wherein the conductive material of the wall is non-porous. 62. 60. The device of claim 59, wherein at least a portion of the wall is free of conductive material. 63. 43. At least a part of the wall has no conductive material. Or 43 or 44 or 45 or 46 or 47 or 48. 64. Walls include distal and proximal zones, with superporous material occupying more of the distal zone than the proximal zone 40 or 41 or 42 or 43 or 44 or 45 or 46 or 47 or The apparatus according to 48. 65. 65. The device of claim 64, wherein at least one third of the proximal region is not porous. . 66. 65. The device of claim 64, wherein the superporous material occupies at least one third of the terminal area. Place. 67. 42. The device according to claim 40, further comprising a radiopaque material held by the electrode. Or 42 or 43 or 44 or 45 or 46 or 47 or 48. 68. Further, based at least in part on the desired physiological effect, the porous element 42. A method according to claim 40, further comprising a controller including means for defining the electrical resistance of the material. The apparatus according to 42 or 43 or 44 or 45 or 46 or 47 or 48. 69. Further, a first electrical resistor of the porous material is provided to achieve a first tissue damage feature. Achieve a second tissue damage characteristic different from the first tissue damage characteristic while defining the resistance A means for defining a second electrical resistance different from the first electrical resistance to 40 or 41 or 42 or 44 or 45 or 47 or 4 including a trawler. An apparatus according to claim 8. 70. Further, the first electrical resistance of the porous material may be reduced to achieve a deep tissue damage shape. To achieve a shallow tissue damage shape, 46. A controller as claimed in claim 42, comprising a controller for defining a second electrical resistance. An apparatus according to claim 8. 71. In addition, a temperature sensing element held on the electrodes, and even less And in part, based on the temperature sensed by the temperature sensing element. 43. A system according to claim 40 or 41 or 42, comprising a controller that regulates the transfer of energy. Or 43 or 44 or 45 or 46 or 47 or 48. 72. 45. The porous material is hydrophilic, 40 or 41 or 42 or 43 or 44. Or the apparatus of 45 or 46 or 47 or 48. 73. A wall comprising a distal region and a proximal region, surrounding the interior region An elongated shape having a large diameter and a fold having a second diameter smaller than the first maximum diameter A structure with a wall mounted so that the collapsed shape can be selected, An internal region capable of holding an ion-containing medium; An element used to electrically connect a medium contained in the inner area to electric energy. And The walls are formed in a size that allows the ions contained in the medium to pass through, Porous that allows ionic transport of electrical energy from a liquid source to the exterior of the wall through the section Part, the porous part of which is occupied more in the terminal area than in the proximal area of the wall Brie. 74. 74. The porous electrode of claim 73, wherein at least one-third of the proximal region of the wall is free of holes. Assembly. 75. First and second porous portions separated by at least a third region without pores; 74. The porous electrode assembly according to claim 73, comprising a second porous region. 76. The structure includes an axis, and the first and second porous regions extend about the axis. 76. The porous electrode according to claim 75, wherein the porous electrode is separately arranged via a third region. Assembly. 77. The structure includes an axis, and the first and second porous regions extend along the axis. 76. The porous electrode according to claim 75, wherein the porous electrode is separately arranged via the third region. Assembly. 78. 74. The porous electrode assembly according to claim 73, wherein the wall is conductive. 79. 74. The apparatus of claim 73, further comprising a radiopaque element carried by the structure. A porous electrode assembly as described. 80. 74. The porosity of claim 73, wherein the medium carries a radiopaque contrast material. Quality electrode assembly. 81. 74. The electrical resistance of the porous portion is at least about 500 ohm-cm. The porous electrode assembly described above. 82. 74. The multi-cell according to claim 73, wherein the electric resistance of the porous portion is about 500 Ω · cm or less. Porous electrode assembly. 83. 74. The porous electrode assembly according to claim 73, wherein the medium comprises a hypertonic solution. 84. 84. The porous electrode assembly of claim 83, wherein the hypertonic solution comprises sodium chloride. - 85. 85. The porous electrode of claim 84, wherein the concentration of sodium chloride is at or near saturation. Assembly. 86. 85. The method of claim 84, wherein the concentration of sodium chloride is up to 9% w / v. Porous electrode assembly. 87. 85. The porous electrode assembly according to claim 84, wherein the hypertonic solution comprises potassium chloride. 88. 74. The porous electrode of claim 73, wherein at least one-third of the proximal region of the wall is free of holes. Assembly. 89. An element is mounted to carry electrical energy and has an internal area 74. The porous electrode assembly according to claim 73, comprising a conductive electrode held on the substrate. 90. 90. The porous electrode assembly according to claim 89, wherein the conductive electrode comprises a noble metal. . 91. Conductive electrodes consist of gold, platinum and platinum / iridium, with essential components 90. The porous electrode according to claim 89, comprising a material selected from a group or a combination thereof. Pole assembly. 92. 74. The porous electrode assembly according to claim 73, wherein the porous portion is hydrophilic. 93. The medium occupies the internal area under internal pressure, and the porous part sets the bubble point value. 94. The porosity of claim 92, wherein the bubble point value is greater than or equal to the internal pressure. Quality electrode assembly. 94. 74. The porous electrode assembly according to claim 73, wherein the porous portion is hydrophobic. 95. The medium occupies the internal area under internal pressure, the porous part has a value of the bubble point 95. The porosity of claim 94, wherein the value of the bubble point is less than or equal to the internal pressure. Quality electrode assembly. 96. The medium occupies the internal area under internal pressure, the porous part has a value of the bubble point 74. The porous electrode according to claim 73, wherein the value of the bubble point is equal to or higher than the internal pressure. Assembly. 97. The medium occupies the internal area under internal pressure, the porous part has a value of the bubble point 74. The porosity according to claim 73, wherein the value of the bubble point is equal to or less than the internal pressure. Quality electrode assembly. 98. 74. The porous electrode assembly according to claim 73, wherein the porous portion includes a hydrophilic coating. 99. 74. The porous electrode of claim 73, wherein the walls are hydrophobic and the porous portion comprises a hydrophilic coating. Assembly. 100. 74. The porous electrode assembly according to claim 73, wherein the porous portion is made of a super porous material. Lee. 101. 74. The porous electrode assembly according to claim 73, wherein the porous portion is made of a microporous material. Lee. 102. A catheter tube having a distal end; A return electrode; A liquid source of the ion-containing medium; Above the catheter tube end and in electrical communication with the return electrode through the tissue Porous electrode, comprising a terminal region and a proximal region, surrounding the inner region. The elongated shape having a first maximum diameter and a second diameter smaller than the first maximum diameter. A wall mounted to select between a folded shape having The interior area and a lumen in fluid communication with the liquid source for transporting the medium to the interior area. Porous electrode and its walls occupy more of the distal zone than the proximal zone and are contained in the medium. A porous portion formed in a size that allows ions to pass through, And a means for coupling the medium in the interior region with the source of electrical energy, wherein the return electrode The conductive electrode is transported to the return electrode to heat the tissue between the Enables ion transport of electrical energy from the element to the exterior of the wall through the medium A living tissue heating device comprising a connecting means. 103. A catheter tube having a distal end; A return electrode; A liquid source of the ion-containing medium; Above catheter tube end, electrically coupled to return electrode through tissue A porous electrode, consisting of a distal region and a proximal region, surrounding the inner region and An elongated shape having a first maximum diameter and a second diameter smaller than the first maximum diameter. A wall mounted so as to select between a collapsed shape and a With a porous portion formed in a size that allows the ions contained in the Wall occupying more of the distal zone than the proximal zone, and for transporting the ion-containing medium to the inner zone A porous electrode comprising a lumen for communicating the internal region with the liquid source, Means for coupling the medium in the interior region with the source of electrical energy, comprising a return electrode and a porous Conductive element for delivery to the return electrode to ablate tissue between the electrodes Means for allowing ionic transport of electrical energy from the medium through the medium to the exterior of the wall A biological tissue resection device comprising: 104. A catheter tube having a deployment end in the atrioventricular chamber of the heart; A return electrode; A liquid source of the ion-containing medium; Above catheter tubing end, electrically coupled to return electrode through heart tissue Is a porous electrode that consists of a terminal region and a proximal region and surrounds the inner region. An elongated shape having a first maximum diameter and a second diameter smaller than the first maximum diameter A wall mounted so as to be selectable with a folded shape having A porous portion formed to have a size that allows ions contained in the medium to pass therethrough; Porous wall occupies more terminal area than proximal area and transports ion-containing medium to internal area A porous electrode consisting of a lumen for communicating the inner region with the liquid source for Means for coupling the medium in the interior region with the source of electrical energy, comprising a return electrode and a porous The conductive element is transported to the return electrode to ablate the heart tissue between the electrodes. That allow ionic transport of electrical energy from the wall through the medium to the exterior of the wall Biological tissue excision device comprising: 105. 95. A hole in at least one third of the proximal area of the wall. An apparatus according to claim 1. 106. A first portion having a porous portion separated by at least a third region having no pores; 105. The porous material according to claim 102, comprising a second porous region. Electrode assembly. 107. The structure includes an axis, and the first and second porous regions are configured to rotate about the axis. 107. The porous electrode according to claim 106, wherein the porous electrode is separately arranged via a third region. Pole assembly. 108. The structure includes an axis, and the first and second porous regions are along the axis. 107. The porous electrode according to claim 106, wherein the porous electrode is separated and disposed via the third region. Pole assembly. 109. 105. The device according to claim 102 or 103 or 104, wherein the wall is conductive. 110. 2. The method of claim 1, further comprising a radiopaque element carried by the structure. 102. The apparatus according to 02 or 103 or 104. 111. A medium comprising a radiopaque contrast material. 105. The apparatus according to 3 or 104. 112. The electrical resistance of the porous portion is at least about 500 ohm-cm. The apparatus according to 2 or 103 or 104. 113. 102. The electric resistance of the porous portion is about 500 Ω · cm or less. 103. The apparatus according to 103 or 104. 114. 105. The apparatus according to claim 102 or 103 or 104, wherein the medium comprises a hypertonic solution. Place. 115. 115. The device of claim 114, wherein the hypertonic solution comprises sodium chloride. 116. 115. The apparatus of claim 115, wherein the concentration of sodium chloride is at or near saturation. 117. 115. The concentration of sodium chloride is at most 9% w / v. Equipment. 118. 105. The hypertonic solution according to claim 102 or 103 or 104, comprising potassium chloride. Equipment. 119. 102. The medium of claim 102 or 103, wherein the resistance of the medium is about 150 Ωcm or less. 104. The apparatus according to 104. 120. 120. The apparatus of claim 119, wherein the medium has a resistance of about 10 ohm-cm or less. 121. 120. The apparatus of claim 119, wherein the medium has a resistance of about 5 ohm-cm or less. 122. 2. The medium of claim 1, wherein the medium comprises a material whose presence increases the viscosity of the medium. 102. The apparatus according to 02 or 103 or 104. 123. The medium is provided with at least one such material that increases the viscosity of the medium due to its presence. 105. Apparatus according to claim 102 or 103 or 104 comprising an on-material. 124. The at least one ionic material comprises a radiopaque material. 114. The apparatus according to 113. 125. The medium contains a non-ionic material whose presence increases the viscosity of the medium Apparatus according to claim 102 or 103 or 104. 126. 126. The device according to claim 125, wherein the non-ionic material comprises glycerol. 127. 126. The device according to claim 125, wherein the non-ionic material comprises mannitol. 128. 104. The porous portion is made of a super porous material. An apparatus according to claim 1. 129. 104. The porous portion is made of a microporous material. An apparatus according to claim 1. 130. In addition, based at least in part on desired physiological effects, Controller with means to regulate the transport of ions through the Apparatus according to claim 102 or 103 comprising a device. 131. The controller is based at least in part on the desired physiological effect To define the pressure differential across the porous area to achieve the desired liquid perfusion rate 130. The device according to claim 130, comprising means. 132. The controller is based at least in part on the desired physiological effect And a means to define that the medium is configured to have the desired viscosity. 130. The apparatus according to claim 130. 133. Further, the controller may be configured to at least partially achieve a desired physiological effect. 102. A means for defining the electric resistance of the porous portion based on Or the apparatus of 104. 134. Further, the first electrical resistance of the porous portion to achieve a first tissue damage feature. Achieve a second tissue damage characteristic different from the first tissue damage characteristic while defining the resistance A means for defining a second electrical resistance different from the first electrical resistance to 105. Apparatus according to claim 103 or 104, comprising a trawler. 135. Further, the first electrical resistance of the porous portion is achieved to achieve a deep tissue damage shape. To achieve a shallow tissue damage shape, 104. A controller comprising a controller for defining a second electrical resistance. An apparatus according to claim 1. 136. Furthermore, a temperature sensing element held by the electrodes, and, furthermore, Based, at least in part, on the temperature sensed by the temperature sensing element. 11. A device according to claim 9 including a controller that regulates the transfer of energy to the body. 105. The apparatus according to 3 or 104. 137. 105. The device according to claim 102, 103 or 104, wherein the porous portion is hydrophilic. Place. 138. The medium occupies the internal area under internal pressure and the porous part has a bubble point value. 137. The apparatus of claim 137, wherein said bubble point value is greater than said internal pressure. 139. 105. The porous part according to claim 102 or 103 or 104, wherein the porous part is hydrophobic. apparatus. 140. The medium occupies the internal area under internal pressure and the porous part has a bubble point value. 139. The method of claim 139, wherein the value of the bubble point is equal to or less than the internal pressure. On-board equipment. 141. The medium occupies the internal area under internal pressure and the porous part has a bubble point value. 102. The bubble point value is greater than the internal pressure. The device according to 04. 142. The medium occupies the internal area under internal pressure and the porous part has a bubble point value. And the value of the bubble point is equal to or less than the internal pressure. The apparatus according to 103 or 104. 143. 105. The porous part comprises a hydrophobic coating film according to claim 102, 103 or 104. Equipment. 144. The wall is hydrophobic, and the porous portion includes a hydrophilic coating. 105. The apparatus according to 3 or 104. 145. 104. The porous portion is made of a super porous material. An apparatus according to claim 1. 146. 104. The porous portion is made of a microporous material. An apparatus according to claim 1. 147. A wall surrounding the interior area, A lumen for transporting the medium to an interior region capable of holding the ion-containing medium; The medium in the interior region comprises an element capable of coupling an electric energy source, Is the wall made of a porous material of a size that allows ions contained in the medium to pass through? A liquid source through the medium and the porous material, comprising at least two separate regions comprising Electrode assembly capable of ion transport of electrical energy from the wall to the exterior of the wall . 148. A wall surrounding an interior region capable of holding an ion-containing medium; An element capable of coupling a medium and an electric energy source, Is the wall made of a porous material of a size that allows ions contained in the medium to pass through? A liquid source through the medium and the porous material, comprising at least two separate regions comprising Electrode assembly capable of ion transport of electrical energy from the wall to the exterior of the wall . 149. A wall surrounding the interior area, A radio frequency energy generator; A lumen that communicates the interior region with the liquid source to carry the ion-containing medium to the interior region When, Can be coupled to the generator to make an electrical connection between the medium in the inner area and the generator Consisting of elements Is the wall made of a porous material of a size that allows ions contained in the medium to pass through? A generator comprising at least two separate regions comprising Porosity capable of transporting radio frequency energy by ions from the outside to the wall Quality electrode assembly. 150. A wall surrounding the interior area, Able to combine the electric energy source with the medium in the internal area that can hold the ion-containing medium Elements and The walls are formed in a size that allows the ions contained in the medium to pass through, A material that allows the ion transport of electrical energy from the liquid source through the material to the exterior of the wall At least two separate regions of porous material, Within an interior area operatively oriented in cooperation with a separately located area A group of aspirates, which can hold a medium by contacting a porous material; A lumen that communicates with each of the gastrointestinal tracts, and transports the ion-containing medium into each of the gastric nose. A porous electrode assembly comprising a transportable lumen. 151. Through a third region made of a material that impedes the passage of ions contained in the medium 147 or 148 or 149, wherein at least two regions are separated. Or the assembly of 150. 152. The wall extends around an axis and the first and second regions extend circumferentially around that axis. 149. The method according to claim 147 or 148 or 149 or 150, which is arranged separately. Assembly. 153. The wall extends around an axis and the first and second regions are separated along that axis 150. The assembly of claim 147 or 148 or 149 or 150, wherein the assembly is disposed. Lee. 154. Walls include distal and proximal zones, with porous material occupying more of the distal zone than proximal zone 150. The assembly of claim 147 or 148 or 149 or 150. 155. 157. The method of claim 154, wherein at least one third of the proximal region is not porous. Assembly. 156. 154. The porous material of claim 154, wherein the porous material occupies at least one-third of the terminal area. Assembly. 157. The wall has an elongated shape having a first maximum diameter and a first shape smaller than the first maximum diameter. 15. A folded configuration having a diameter of two and optionally mounted. 170. The assembly according to 7 or 148 or 149 or 150. 158. In addition, when the form changes, along a predetermined fold line Including at least one folding area on a wall mounted to fold itself 157. The assembly of claim 157. 159. 157. The fold line is generally provided between the two regions. On-board assembly. 160. 157. The method according to claim 157, wherein the folding area is not porous through which ions can pass. Assembly. 161. 160. The assembly of claim 157, wherein the fold area is substantially free of conductive material. Lee. 162. Claims further comprising at least one temperature sensing element retained on the wall 147. The assembly according to clause 147 or 148 or 149 or 150. 163. At least one temperature in proximity to at least one region of the porous material; 163. The assembly of claim 162, wherein the sensing element is disposed. 164. At least one temperature sensing element is provided in at least one region of the porous material. 163. The assembly of claim 162, wherein the element is disposed. 165. The porous material area has an edge boundary and at least one edge boundary 163. The assembly of claim 162, wherein at least one temperature sensing element is disposed. . 166. A porous material that allows ions to pass while blocking blood cells 147. The method according to claim 147, 148, 149 or 150, which is sized. Assembly. 167. The porous material allows ions to pass while blocking polymers 147 or 148 or 149 or 150 formed in a suitable size. Assembly. 168. 147. 147 or 148 or 149, wherein the porous material comprises an ultrafiltration membrane. The assembly according to 150. 169. 147. 147 or 148 or 149 or the porous material comprises a microporous membrane. The assembly according to 150. 170. 147. The element of claim 147 or wherein the element comprises a conductive electrode in the interior region of the wall. 150. The assembly according to 148 or 149 or 150. 171. 170. The assembly of claim 170, wherein the conductive electrode comprises a noble metal. 172. The conductive electrode is made of gold, platinum and platinum / iridium as essential components. 170. The assembly according to claim 170, comprising a material selected from the group consisting of: Mumburi. 173. 147. 147 or 148 or 149 or 150 wherein the medium comprises a hypertonic solution. The described assembly. 174. 173. The assembly of claim 173, wherein the hypertonic solution comprises sodium chloride. 175. 173. The assay according to claim 173, wherein the concentration of sodium chloride is at or near saturation. Mumburi. 176. 173. The concentration of sodium chloride is up to about 9% w / v. On-board assembly. 177. 173. The assembly of claim 173, wherein the hypertonic solution comprises potassium chloride. 178. 148. The medium of claim 147 or 148, wherein the medium has a resistance of about 150 Ωcm or less. 150. The assembly according to 149 or 150. 179. 178. The assembly of claim 178, wherein the medium has a resistance of about 10 ohm-cm or less. Lee. 180. 178. The assembly of claim 178, wherein the medium has a resistance of about 5 ohm-cm. 181. 15. The medium of claim 14, wherein the medium comprises a material whose presence increases the viscosity of the medium. 170. The assembly according to 7 or 148 or 149 or 150. 182. The medium has at least one ion, the presence of which increases the viscosity of the medium. 147. The assembly according to claim 147 or 148 or 149 or 150, comprising an elastic material. Lee. 183. The at least one ionic material comprises a radiopaque material. 82. The assembly according to 82. 184. The medium contains a non-ionic material whose presence increases the viscosity of the medium 150. The assembly of claim 147 or 148 or 149 or 150. 185. 184. The assembly of claim 184, wherein the non-ionic material comprises glycerol. . 186. 187. The assembly of claim 184, wherein the non-ionic material comprises mannitol. 187. The electrical resistance of the porous material is at least about 500 ohm-cm. 170. The assembly according to 7 or 148 or 149 or 150. 188. 147. The electric resistance of the porous material is about 500Ω · cm or less. 150. The assembly according to 148 or 149 or 150. 189. 147. 147 or 148 or 1 wherein at least part of the wall contains a conductive material. 150. The assembly according to 49 or 150. 190. 190. 189. The conductive material of the wall is porous allowing ions to pass through. Assembly. 191. 189. The conductive material of the wall is non-porous, impervious to ions. The described assembly. 192. 189. The method of claim 189, wherein the conductive material comprises a coating applied to a wall. Assembly. 193. 189. The assembly of claim 189, wherein the conductive material comprises a foil attached to a wall. . 194. 189. The assembly of claim 189, wherein the conductive material is disposed in the wall. . 195. Conductive material must not be exposed from uninsulated signal wires exposed on the outer surface of the wall. 189. The assembly of claim 189. 196. 189. The assembly of claim 189, wherein at least a portion of the wall is free of conductive material. Brie. 197. 147. 147 or 148 or at least part of the wall is free of conductive material. 150. The assembly according to 149 or 150. 198. In addition, assembled within the interior area to form a support structure under the wall 150. The assembly according to claim 147 or 148 or 149 or 150, comprising a member to be assembled. Brie. 199. 200. The assembly of claim 198, wherein the solid support member comprises a metal material. 200. 200. The assembly of claim 199, wherein the metallic material comprises nickel titanium. 201. 200. The assembly of claim 199, wherein the metallic material comprises stainless steel. 202. 198. The assembly of claim 198, wherein the solid support member comprises a plastic material. Brie. 203. Solid support members are assembled and stretched at regular intervals in the circumferential direction. 198. The assembly of claim 198, comprising a splined member. 204. 199. The assembly of claim 198, wherein the solid support member comprises a porous foam. Brie. 205. Further comprising a radiopaque material retained in the assembly. 147 or 148 or 149 or 150. 206. 147 or 148 or 149 or 15 wherein the porous material is hydrophilic. Assembly according to 0. 207. The medium occupies the internal area under internal pressure, and the porous material is at the pressure at the bubble point 210. The assembly of claim 206, wherein the pressure value at the bubble point is greater than the internal pressure. Mumburi. 208. 147 or 148 or 149 or 15 wherein the porous material is hydrophobic. Assembly according to 0. 209. The medium occupies the internal area under internal pressure, and the porous material is at the pressure at the bubble point 3. The pressure value at the bubble point is equal to or less than the internal pressure. 08. Assembly according to 08. 210. The medium occupies the internal area under internal pressure, and the porous material is at the pressure at the bubble point 147 or 148, wherein the pressure value at the bubble point is greater than the internal pressure. Or the assembly of 149 or 150. 211. The medium occupies the internal area under internal pressure, and the porous material is at the pressure at the bubble point The pressure value at the bubble point is equal to or less than the internal pressure. 150. The assembly according to 47 or 148 or 149 or 150. 212. 147 or 148 or 149 or the porous material comprises a hydrophilic coating. 150. The assembly according to 150. 213. 147. 147 or 148 wherein the wall is hydrophobic and the porous material comprises a hydrophilic coating. Or the assembly of 149 or 150. 214. A catheter tube having a distal end; A return electrode; A liquid source of the ion-containing medium; Above catheter tube end, electrically coupled to return electrode through tissue An electrode, a wall having an outer surface surrounding the periphery of the inner region; An electrode consisting of a lumen carrying the ion-containing medium and a conductive element in the interior area When, Means for connecting the conductive element to an energy source for transmitting energy; Is the wall made of a porous material of a size that allows ions contained in the medium to pass through? A pair between the return electrode and the porous electrode, comprising at least two separate regions comprising The medium and porous material from a liquid source are transported to a return electrode to heat the fabric. A wall that allows electrical energy to be transported by ions to the outside of the communicating wall. And according to predetermined criteria, the electrical energy can be Controller that combines a liquid source with an energy source to control the transport of energy A living tissue heating device comprising: 215. A catheter tube having a distal end; A return electrode; A liquid source of the ion-containing medium; Above catheter tube end, electrically coupled to return electrode through tissue An electrode, a wall having an outer surface surrounding the periphery of the inner region; An electrode consisting of a lumen carrying the ion-containing medium and a conductive element in the interior area When, Means for connecting the conductive element to an energy source for transmitting energy; Is the wall made of a porous material of a size that allows ions contained in the medium to pass through? A pair between the return electrode and the porous electrode, comprising at least two separate regions comprising The media and porous material from the liquid source are transported to the return electrode to cut the weave. A wall that allows electrical energy to be transported by ions to the outside of the communicating wall. And according to predetermined criteria, the electrical energy can be Controller that combines a liquid source with an energy source to control the transport of energy A biological tissue resection device comprising: 216. A catheter tube having a deployment end in the atrioventricular chamber of the heart; A return electrode; A liquid source of the ion-containing medium; Above catheter tubing end, electrically coupled to return electrode through heart tissue A wall having an outer surface surrounding the perimeter of the inner region; Consisting of a lumen carrying the ion-containing medium to the region and a conductive element in the interior region Electrodes and Means for connecting the conductive element to an energy source for transmitting energy; Is the wall made of a porous material of a size that allows ions contained in the medium to pass through? A core between the return electrode and the porous electrode. Media and porous material from a liquid source for delivery to the return electrode for ablation of visceral tissue A wall capable of transporting electrical energy by ions to the outside of the wall through the material And, according to predetermined criteria, the electrical energy in A controller that combines liquid and energy sources to control energy transport Heart tissue resection device consisting of 217. Further comprising at least one temperature sensing element on the wall; and The controller detects the temperature detected at least in part by the temperature sensing element. Control the transfer of electrical energy from separately located areas based on degree 229. Apparatus according to claim 214 or 215 or 216 comprising means. 218. At least one temperature sensing element is in proximity to at least one of the regions 218. The apparatus according to claim 217, wherein 219. At least one temperature sensing element is located at least in the area. 228. The apparatus of claim 217, wherein 220. The area of the porous material has an edge boundary and at least one temperature sensing element. 218. The element is located along at least one edge boundary. Equipment. 221. The controller is based at least in part on the desired physiological effect 214 or 215 or 216 comprising means for defining the electrical resistance of the region by means of The described device. 222. Further, the controller can be configured to perform the first tissue damage feature to achieve the first tissue damage feature. A second tissue that defines a first electrical resistance of the second tissue and is different from the first tissue damage feature. Means for defining a second electrical resistance different from the first electrical resistance to achieve the damage feature 229. The apparatus according to claim 215 or 216, comprising a step. 223. A controller may be configured to provide a first electrical power to the region to achieve a deep tissue lesion shape. The first electrical resistance to define the air resistance and to achieve a shallow tissue damage shape 226. The method of claim 215 or 216, further comprising means for defining a greater second electrical resistance. Equipment. 224. Further comprising a radiopaque material held by the electrode. 215. The apparatus according to 215 or 216. 225. 217. The porous material according to claim 214 or 215 or 216, wherein the porous material is hydrophilic. Equipment. 226. The medium occupies the internal area under internal pressure, and the porous material is the pressure value at the bubble point 220. The apparatus of claim 215, wherein the pressure value at the bubble point is greater than the internal pressure. 227. 220. The porous material of claim 214 or 215 or 216, wherein the porous material is hydrophobic. apparatus. 228. The medium occupies the internal area under internal pressure, and the porous material is at the pressure at the bubble point 3. The pressure value at the bubble point is equal to or less than the internal pressure. 16. The apparatus according to claim 15. 229. The medium occupies the internal area under internal pressure, and the porous material is at the pressure at the bubble point 214 or 215, wherein the pressure value at the bubble point is greater than the internal pressure. Or the apparatus of 216. 230. The medium occupies the internal area under internal pressure, and the porous material is at the pressure at the bubble point 3. The pressure value at the bubble point is equal to or less than the internal pressure. 214. The apparatus according to 14 or 215 or 216. 231. 220. The porous material of claim 214 or 215 or 216, wherein the porous material comprises a hydrophilic coating. The described device. 232. 214.The wall is hydrophobic and the porous material comprises a hydrophilic coating. 215. The apparatus according to 215 or 216. 233. A wall having an interior area and a conductive element in the interior area; At least some of its walls allow ions to pass while blocking blood cells from passing. A porous electrode made of a porous material formed in the size; A conductive element for coupling the conductive element and a source of electrical energy; Ion transfer of electrical energy through a liquid medium and porous material to ablate tissue Liquid conductive element for transporting an ion-containing liquid medium to an internal area by allowing transport And Define different electrical resistances of the porous material to achieve the required tissue resection effect identification Biological tissue excision device comprising: 234. A wall having an interior area and a conductive element in the interior area; At least some of its walls allow ions to pass while blocking blood cells from passing. A porous electrode made of a porous material formed in the size; A conductive element for coupling the conductive element and a source of electrical energy; Ion transfer of electrical energy through a liquid medium and porous material to ablate tissue Liquid conductive element for transporting an ion-containing liquid medium to an internal area by allowing transport And To achieve a first damage feature, a first electrical resistance of the porous material is defined and In order to achieve a second damage characteristic different from the first damage characteristic, Means for defining the electrical resistance of a living tissue for forming a lesion. 235. A wall having an interior area and a conductive element in the interior area; At least some of its walls allow ions to pass while blocking blood cells from passing. A porous electrode made of a porous material formed in the size; A conductive element for coupling the conductive element and a source of electrical energy; Ion transfer of electrical energy through a liquid medium and porous material to ablate tissue Liquid conductive element for transporting an ion-containing liquid medium to an internal area by allowing transport And To achieve a deep tissue damage shape, the first electrical resistance of the porous material should be defined. In particular, a second electrical resistance of the porous material is defined to achieve a shallow tissue damage shape. Biological tissue resection device for lesion formation. 236. Furthermore, a temperature sensing element held by the porous electrode is provided. , Based at least in part on the temperature sensed by the temperature sensing element, 233 or 234 or 23 comprising means for delivering electrical energy to the medium. An apparatus according to claim 5. 237. 233, 234, or 235, wherein the porous material comprises a microporous membrane. An apparatus according to claim 1. 238. 233, 234, or 235, wherein the porous material comprises an ultrafiltration membrane. An apparatus according to claim 1. 239. The wall has a proximal region and a distal region, and the porous material is more distal than the proximal region. 237. The apparatus according to claim 233 or 234 or 235 occupying a large area. 240. 239. The device of claim 239, wherein at least one-third of the proximal region of the wall is free of holes. 241. The porous portion of the wall is separated and arranged via at least a third region without pores. 233 or 234 or 235 comprising first and second porous regions disposed therein. An apparatus according to claim 1. 242. The electrode includes an axis, and a first and a second area around the axis via a third region. 241. The apparatus of claim 241, wherein the two porous regions are circumferentially separated. 243. The electrode includes an axis and along the axis a first and a large area via a third region. 241. The apparatus of claim 241, wherein the two porous regions are spaced apart. 244. 237. The apparatus of claim 233 or 234 or 235, wherein the wall is conductive. 245. 24. The device further comprising a radiopaque element carried on the electrode. The device of claim 3 or 234 or 235. 246. 233. The medium of claim 233, further comprising a radiopaque contrast material. 234 or 235. 247. The porous part has a porosity that provides an electric resistance of at least about 500 Ωcm. 237. The apparatus of claim 233 or 234 or 235. 248. The porous part has a porosity that gives an electric resistance of about 500 Ω · cm or less. 233. The apparatus according to claim 233 or 234 or 235. 249. 237. The apparatus according to claim 233 or 234 or 235, wherein the medium comprises a hypertonic solution. . 250. 249. The device according to claim 249, wherein the hypertonic solution comprises sodium chloride. 251. The device of claim 250, wherein the concentration of sodium chloride is at or near saturation. 252. 250. The concentration of sodium chloride is up to 9% w / v. Equipment. 253. 249. The device according to claim 249, wherein the hypertonic solution comprises potassium chloride. 254. 233. The medium of claim 233 or 234, wherein the medium has a resistance of about 150 Ωcm or less. 235. The apparatus according to 235. 255. 254. The apparatus of claim 254, wherein the medium has a resistance of about 10 ohm-cm or less. 256. 254. The apparatus of claim 254, wherein the medium has a resistance of about 5 ohm-cm or less. 257. 24. The medium comprises a material whose presence increases the viscosity of the medium. Device according to 3 or 234 or 235. 258. The medium has at least one ion, the presence of which increases the viscosity of the medium. 237. The apparatus according to claim 233, 234 or 235, comprising a conductive material. 259. A contract made of at least one ionic material made of a radiopaque material 258. The apparatus of claim 258. 260. The medium contains a non-ionic material whose presence increases the viscosity of the medium Apparatus according to claim 233 or 234 or 235. 261. The device of claim 260, wherein the non-ionic material comprises glycerol. 262. The device of claim 260, wherein the non-ionic material comprises mannitol. 263. Further, based at least in part on the desired physiological effect on the tissue, And means for defining ion transport through the porous material at a desired rate. 233. The apparatus according to 234 or 235. 264. 233, 234, or 235, wherein the porous material comprises an ultrafiltration membrane. An apparatus according to claim 1. 265. 233 or 234 or 235, wherein the porous portion comprises a microporous membrane. The described device. 266. Further, based at least in part on the desired physiological effects on the tissue, 233 or 234 or that the medium has the desired viscosity 235. The apparatus according to claim 235. 267. A wall surrounding the interior area, A lumen capable of transporting the medium to an interior region capable of holding the ion-containing medium, An element for coupling the energy source with the medium in the interior area; At least part of the wall is used to transfer electrical energy from the liquid source to the medium and porous material. The ions contained in the medium are removed so that they can be transported by the ions to the outside of the street wall. It is made of a porous material formed in a size that can pass through, Then, at least one temperature sensing element that contacts the outside of the wall and is held by the wall. And a porous electrode assembly. 268. A wall surrounding an interior region capable of holding an ion-containing medium; An element that connects the medium with an electrical energy source, At least part of the wall is used to transfer electrical energy from the liquid source to the medium and porous material. The ions contained in the medium are removed so that they can be transported by the ions to the outside of the street wall. It is made of a porous material formed in a size that can pass through, Then, at least one temperature sensing element that contacts the outside of the wall and is held by the wall. And a porous electrode assembly. 269. A wall surrounding the interior area, A radio frequency energy generator; A liquid source holding an ion-containing medium; A lumen in communication between the interior region and the liquid source for carrying the ion-containing medium to the interior region; When, In order to make electrical contact between the medium in the internal area and the generator, Elements and At least part of the wall is used to transfer electrical energy from the liquid source to the medium and porous material. The ions contained in the medium are removed so that they can be transported by the ions to the outside of the street wall. It is made of a porous material formed in a size that can pass through, Then, at least one temperature sensing element that contacts the outside of the wall and is held by the wall. And a porous electrode assembly. 270. 267 or 268 or 269, wherein the porous material comprises an ultrafiltration membrane. 4. The porous electrode assembly according to item 1. 271. 267 or 268 or 269, wherein the porous material comprises a microporous membrane. 4. The porous electrode assembly according to item 1. 272. 267 or the element comprises a conductive electrode in the interior region of the wall 268. The porous electrode assembly according to 268 or 269. 273. 273. The assembly of claim 272, wherein the conductive electrode comprises a noble metal. 274. The conductive electrode is made of gold, platinum and platinum / iridium as essential components. 272. includes a material selected from the group consisting of: The described assembly. 275. 270. The method according to claim 267 or 268 or 269, wherein the medium comprises a hypertonic solution. Assembly. 276. 275. The assembly of claim 275, wherein the hypertonic solution comprises sodium chloride. 277. 280. The process according to claim 276, wherein the concentration of sodium chloride is saturated or near. Mumburi. 278. The concentration of sodium chloride is up to about 9% w / v. Assembly. 279. 275. The assembly of claim 275, wherein the hypertonic solution comprises potassium chloride. 280. 267 or 268. The medium of claim 267 or 268, Is the assembly according to 269. 281. 267 or 268 or wherein the resistance of the medium is no greater than about 10 ohm-cm. 269. The assembly of claim 269. 282. 267 or 268 or 269, wherein the resistance of the medium is about 5 ohm-cm. An assembly according to claim 1. 283. 267. The medium comprises a material whose presence increases the viscosity of the medium. Or the assembly of 268 or 269. 284. At least one ion whose medium increases the viscosity of the medium due to its presence 267. The assembly according to claim 267 or 268 or 269, comprising a conductive material. 285. The at least one ionic material comprises a radiopaque material. 284. The assembly of claim 284. 286. The medium contains a nonionic material whose presence increases the viscosity of the medium. 269. The assembly of claim 267 or 268 or 269. 287. 289. The assembly of claim 286, wherein the non-ionic material comprises glycerol. . 288. 289. The assembly of claim 286, wherein the non-ionic material comprises mannitol. 289. 267. The electrical resistance of the porous material is greater than about 500 ohm-cm. Is the assembly according to 268 or 269. 290. 267. The electric resistance of the porous material is about 500 Ω · cm or less. Is the assembly according to 268 or 269. 291. 267 or 268 or at least a portion of the wall comprises a conductive material. 269. The assembly of claim 269. 292. 293. The assembly of claim 291, wherein the conductive material of the wall is porous. 293. 292. The assembly of claim 291, wherein the conductive material of the wall is non-porous. 294. 291. The conductive material of claim 291, wherein the conductive material comprises a coating applied to a wall. Assembly. 295. 292. The assembly of claim 291, wherein the conductive material comprises a foil attached to a wall. - 296. 293. The assembly of claim 291 wherein the conductive material is a protruding portion of the wall. Brie. 297. Conductive material must be free of uninsulated signal wires exposed outside the wall. 292. The assembly of claim 291. 298. 292. The electrode assembly of claim 291, wherein at least a portion of the wall is not a conductive material. Brie. 299. 267 or 268 or 2 wherein at least a part of the wall is not a conductive material. 69. The electrode assembly according to 69. 300. In addition, assembled within the interior area to form a support structure under the wall 267. The electrode assembly according to claim 267 or 268 or 269, comprising a member to be assembled. 301. The assembly of claim 300, wherein the solid support member comprises a metal material. . 302. 302. The assembly of claim 301, wherein the metallic material comprises nickel titanium. 303. 302. The assembly of claim 301, wherein the metallic material comprises stainless steel. 304. 300. The assembly according to claim 300, wherein the solid support member is made of a plastic material. Brie. 305. The solid support members are assembled such that they are in a circumferentially spaced relationship. 300. The assemble of claim 300, comprising a splined element erect and elongated. Lee. 306. The assembly of claim 300, wherein the solid support member comprises a porous foam. . 307. The wall may have a proximal zone and a distal zone, and may include more distal zones than the proximal zone. 267. The assembly of claim 267. 308. 307. The assay of claim 307, wherein at least one third of the proximal region is free of porous material. Mumburi. 309. 304. The method according to claim 307, wherein the porous material occupies at least 1/3 of the terminal area. Assembly. 310. A catheter tube having a distal end; A return electrode; A liquid source of the ion-containing medium; Above the catheter tube end and in electrical communication with the return electrode through the tissue A porous electrode, comprising a distal region and a proximal region, surrounding the inner region, A lumen for transporting the ion-containing medium from the liquid source to the interior region; An electrode comprising an electrically conductive element; Means for coupling the conductive element and the energy source to transfer energy; , At least a part of the wall is formed to be large enough to pass ions contained in the medium. To heat the tissue between the return electrode and the porous electrode Electrical energy from the conductive element through the medium to the exterior of the wall for transport to the return electrode. Energy can be transported by ions, Then, the at least one temperature detecting element is brought into thermal contact with the outside of the wall and held by the wall. A living tissue heating device consisting of a body and a body. 311. A catheter tube having a distal end; A return electrode; A liquid source of the ion-containing medium; Above the catheter tube end and in electrical communication with the return electrode through the tissue A porous electrode, comprising a distal region and a proximal region, surrounding the inner region, A lumen for transporting the ion-containing medium from the liquid source to the interior region; An electrode comprising an electrically conductive element; Means for coupling the conductive element and the energy source to transfer energy; , At least a part of the wall is formed to be large enough to pass ions contained in the medium. To remove the tissue between the return electrode and the porous electrode Electrical energy from the conductive element through the medium to the exterior of the wall for transport to the return electrode. Energy can be transported by ions, Then, the at least one temperature detecting element is brought into thermal contact with the outside of the wall and held by the wall. A living tissue resection device consisting of a body and a body. 312. A catheter tube having a deployment end in the atrioventricular chamber of the heart; A return electrode; A liquid source of the ion-containing medium; Above the catheter tube end and in electrical communication with the return electrode through the tissue A porous electrode, comprising a distal region and a proximal region, surrounding the inner region, A lumen for transporting the ion-containing medium from the liquid source to the interior region; An electrode comprising an electrically conductive element; Means for coupling the conductive element and the energy source to transfer energy; , At least a part of the wall is formed to be large enough to pass ions contained in the medium. Of heart tissue between the return electrode and the porous electrode For transport to the return electrode, the conductive element passes through the medium through the medium to the outside of the wall. Energy can be transported by ions, Then, the at least one temperature detecting element is brought into thermal contact with the outside of the wall and held by the wall. Resection device for heart tissue consisting of elements. 313. 310. The apparatus of claim 310 or 311 or 312, wherein the medium comprises a hypertonic solution. Place. 314. The device of claim 313, wherein the hypertonic solution comprises sodium chloride. 315. 314. The apparatus according to claim 314, wherein the concentration of sodium chloride is at or near saturation. . 316. 314. The concentration of sodium chloride is up to about 9% w / v. On-board equipment. 317. 310. The hypertonic solution according to claim 310 or 311 or 312, comprising potassium chloride. On-board equipment. 318. 317. The apparatus of claim 317, wherein the medium has a resistance of about 150 ohm-cm or less. 319. 317. The apparatus of claim 317, wherein the medium has a resistance of about 10 ohm-cm or less. 320. 317. The apparatus of claim 317, wherein the medium has a resistance of about 5 ohm-cm. 321. 32. The medium comprises a material whose presence increases the viscosity of the medium. The apparatus according to 0 or 311 or 312. 322. At least one ion whose medium increases the viscosity of the medium due to its presence The device of claim 310 or 311 or 312, comprising a conductive material. 323. The at least one ionic material comprises a radiopaque material. 322. The apparatus of claim 322. 324. The medium contains a nonionic material whose presence increases the viscosity of the medium. The apparatus of claim 310 or 311 or 312. 325. The device of claim 324, wherein the non-ionic material comprises glycerol. 326. The device of claim 324, wherein the non-ionic material comprises mannitol. 327. 310. The porous material comprises an ultrafiltration membrane. An apparatus according to claim 1. 328. 310. The porous material comprises a microporous membrane. An apparatus according to claim 1. 329. 310. The electrical resistance of the porous material is greater than about 500 ohm-cm. The apparatus according to 311 or 312. 330. 310. The electrical resistance of the porous material is about 500 Ω · cm or less. The apparatus according to 311 or 312. 331. 310. At least a portion of the wall comprises a conductive material. The device of 312. 332. 331. The device of claim 331, wherein the conductive material of the wall is porous. 333. 331. The device of claim 331, wherein the conductive material of the wall is non-porous. 334. 331. The electrode assembly of claim 331, wherein at least a portion of the wall is not a conductive material. Brie. 335. 310. At least a part of the wall is not a conductive material. 13. The electrode assembly according to claim 12. 336. The wall has a distal zone and a proximal zone, and the porous material occupies more of the distal zone than the proximal zone An electrode assembly according to claim 310 or 311 or 312. 337. 337. The method of claim 336, wherein at least one third of the proximal region is free of porous material. Assembly. 338. 337. The porous material of claim 336, wherein the porous material occupies at least 1/3 of the terminal area. Assembly. 339. A wall surrounding the interior area, at least a part of which is made of conductive material Walls and A lumen that carries the medium to an interior area that can hold the ion-containing medium, And at least a part of the wall is large enough to allow the ions contained in the medium to pass through. An electrode assembly made of the formed porous material. 340. 339. The assembly of claim 339, wherein the porous material is adjacent to the conductive material. 341. In addition, conductive materials are used to transport electrical energy. 339. The assembly of claim 339, comprising an element for connecting to a source. 342. The conductive material is porous, through which ions contained in the medium can pass. 341. The assembly of claim 341. 343. In addition, the ion transport of electrical energy by the medium through the porous material To enable this, a conductive element that couples the medium in the inner area to a source of electrical energy 342. The assembly of claim 341, comprising a component. 344. 4. The conductive element comprises a conductive electrode in the interior region of the wall. 43. The assembly of claim 43. 345. 347. The assembly of claim 344, wherein the conductive electrodes comprise a noble metal. 346. The conductive electrode is made of gold, platinum and platinum / iridium as essential components. 345. A material comprising a material selected from the group consisting of: The described assembly. 347. The conductive material is porous, through which ions contained in the medium can pass. 343. The assembly of 343. 348. In addition, the conductive material for transmitting the signal detected by the conductive material 340. The assembly according to claim 339 or 340, comprising an element coupled to a conductive material. - 349. In addition, conductive materials are used to transport electrical energy. 348. The assembly of claim 348, comprising an element coupled to the source. 350. Make sure that the conductive material is porous and can pass ions contained in the medium. 349. The assembly of claim 349. 351. In addition, the ion transport of electrical energy by the medium through the porous material To enable this, a conductive element that couples the medium in the interior area with a source of electrical energy 349. The assembly of claim 349, comprising an element. 352. 4. The conductive element comprises a conductive electrode in the interior region of the wall. 51. The assembly according to 51. 353. 352. The assembly of claim 352, wherein the conductive electrodes comprise a noble metal. 354. The conductive electrode is made of gold, platinum and platinum / iridium as essential components. 353. A material comprising a material selected from the group consisting of: The described assembly. 355. Make sure that the conductive material is porous and can pass ions contained in the medium. 358. The assembly of claim 353. 356. At least a portion of the wall is made of a conductive material and surrounds the inner area, A lumen capable of transporting the medium into an interior region capable of holding the ion-containing medium; To enable ion transport of electrical energy by the medium, A conductive element capable of coupling with a source of electrical energy, Then, at least a part of the wall is formed by a medium to the outside of the wall through the porous material. Ions contained in the medium pass through to enable ion transport of electrical energy An electrode assembly made of a porous material formed in a possible size. 357. 356. The assembly of claim 356, wherein the porous material is adjacent to the conductive material. 358. In addition, electrical energy sources and conductive 358. The assembly of claim 356 or 357, comprising a material binding element. . 359. Make sure that the conductive material is porous and can pass ions contained in the medium. 358. The assembly of claim 358. 360. In addition, conductive materials that transmit electrical signals detected by conductive materials 358. The assembly of claim 356 or 357, comprising an associated element. 361. In addition, conductive materials are used to transport electrical energy. 360. The assembly of claim 360, comprising an element coupled to the source. 362. Make sure that the conductive material is porous and can pass ions contained in the medium. 361. The assembly of claim 361. 363. 4. The conductive element comprises a conductive electrode in an interior region of the wall. 358. The assembly according to 56 or 357. 364. 363. The assembly of claim 363, wherein the conductive electrode comprises a noble metal. 365. The conductive electrode is made of gold, platinum and platinum / iridium as essential components. 363. A material comprising a material selected from the group consisting of: The described assembly. 366. Claims in which the porous material is sized to block the passage of polymers Item 365. The assembly according to item 365 or 357. 367. 358. The assay device according to claim 356 or 357, wherein the porous material comprises an ultrafiltration membrane. Mumburi. 368. 356. The assay according to claim 356 or 357, wherein the porous material is a microporous membrane. Mumburi. 369. 339. 339 or 356 wherein the conductive material comprises a coating applied to a wall. The described assembly. 370. 339. The method of claim 339 or 356, wherein the conductive material comprises a foil attached to a wall. Assembly. 371. 339. 339 or 356 wherein the conductive material comprises coextruded portions of the wall. An assembly according to claim 1. 372. Conductive material must be free of uninsulated signal wires exposed outside the wall. 339. The assembly of claim 339 or 356. 373. The assembly of claim 339 or 356, wherein the medium comprises a hypertonic solution. . 374. 373. The assembly of claim 373, wherein the hypertonic solution comprises sodium chloride. 375. 374. The assay according to claim 374, wherein the concentration of sodium chloride is at or near saturation. Mumburi. 376. 374. The method of claim 374, wherein the concentration of sodium chloride is up to about 9% w / v. On-board assembly. 377. 373. The assembly of claim 373, wherein the hypertonic solution comprises potassium chloride. 378. 339. The medium of claim 339 or 356, wherein the medium has a resistance of about 150 Ω-cm or less. The described assembly. 379. 339. The medium of claim 339 or 356, wherein the medium has a resistance of about 10 ohm-cm or less. On-board assembly. 380. . 339. The method of claim 339 or 356, wherein the medium has a resistance of about 5 ohm-cm. Assembly. 381. 34. The medium comprises a material whose presence increases the viscosity of the medium. The assembly according to 9 or 356. 382. The medium has at least one ion, the presence of which increases the viscosity of the medium. 339. The assembly of claim 339 or 356, wherein the assembly comprises a functional material. 383. The at least one ionic material comprises a radiopaque material. 382. The assembly of claim 382. 384. The medium contains a non-ionic material whose presence increases the viscosity of the medium An assembly according to claim 339 or 356. 385. 383. The assembly of claim 384, wherein the non-ionic material comprises glycerol. - 386. 383. The assembly of claim 384, wherein the non-ionic material comprises mannitol. . 387. 339. The electric resistance of the porous material is about 500 Ω · cm or more. Is the assembly according to 356. 388. 339. The electric resistance of the porous material is about 500 Ω · cm or less. Is the assembly according to 356. 389. In addition, assembled within the interior area to form a support structure under the wall 339. The assembly according to claim 339 or 356, including an attached member. 390. 389. The assembly of claim 389, wherein the solid support member comprises a metal material. 391. 390. The assembly of claim 390, wherein the metallic material comprises nickel titanium. 392. 390. The assembly of claim 390, wherein the metallic material comprises stainless steel. 393. 390. The assembly according to claim 390, wherein the solid support member is made of a plastic material. Brie. 394. The solid support members are assembled such that they are in a circumferentially spaced relationship. 390. The assemble of claim 390, comprising an erect and splined element. Lee. 395. 390. The assembly of claim 390, wherein the solid support member comprises a porous foam. - 396. The assembly according to claim 339 or 356, wherein the porous material is hydrophilic. Lee. 397. The lumen carries the ion-containing medium to an interior area under internal pressure. 339. The porous material having a bubble point value greater than its internal pressure. Is the assembly according to 356. 398. 397. The assembly of claim 397, wherein the porous material is hydrophilic. 399. An ion-containing medium source; A generator of electrical energy, A wall having an outer surface surrounding the interior area, wherein at least a portion of the wall is electrically A wall of conductive material with a surface area to carry energy, An electrode comprising a lumen for transporting the medium from the liquid source to the interior region of the wall; At least a part of the wall is formed large enough to pass ions contained in the medium. Next to the conductive material made of porous material, Then, an instruction is given to transfer energy from the generator by the conductive material. On the other hand, by instructing the transport of the ion-containing medium from the medium source, the necessary tissue heating can be performed. A controller coupled to the media source and generator to obtain the effect The material creates an effective surface area for transporting electrical energy that is larger than its own surface area Transports electrical energy while enabling the transport of ions through porous materials. A biological tissue heating device comprising a controller that performs heating. 400. In addition, there are conductive elements that connect the medium in the inner area of the wall to the generator. e, And while the conductive material carries the electrical energy, the medium through the porous material To enable ion transport of electrical energy, the electrical energy from the generator The controller transfers the energy to the conductive element for transport to the conductive element. The device of claim 399 coupled to the element. 401. A medium source containing ions; A generator of electrical energy, A wall surrounding an interior area, at least a portion of which carries electrical energy. A wall of conductive material with a surface area for An electrode comprising a lumen that can be transported to the interior region of the wall; At least a part of the wall is formed large enough to pass ions contained in the medium. A wall adjacent to a conductive material made of a porous material, A conductive element capable of connecting the generator with the medium in the interior area of the wall; Conductive material forms an effective surface area for electrical energy transfer that is greater than its surface area To transfer electrical energy through the porous material while transporting it. To enable ion transport, transfer the ion-containing medium from the liquid source to the internal region. While transferring electrical energy from the generator to the element and conductive material Liquid source, generator and element to obtain the desired tissue heating effect. Biological tissue heating device consisting of a controller connected to the 402. The controller heats the desired tissue by ablating the living tissue. 405. Apparatus according to claim 399 or 400 or 401, wherein an effect can be achieved. 403. The controller heats the desired tissue by ablating the heart tissue 405. Apparatus according to claim 399 or 400 or 401, wherein an effect can be achieved. 404. A medium source containing ions; A generator of electrical energy, A processor that processes electrical phenomena in heart tissue; A wall with an outer surface surrounding the interior area, at least a portion of the wall A wall made of conductive material having a surface area for detecting electrical phenomena in tissue And a lumen for transporting the ion-containing medium from the liquid source to the interior region of the wall. And at least a part of the wall is shaped to be able to pass ions contained in the medium. A wall adjacent to the formed conductive material made of a porous material, A controller connected to the liquid source, generator and processor In a first mode, the trawler is used to deliver the heart tissue to a processor. Command the conductive material to detect electrical phenomena in the second mode. Generator to instruct the movement of the ion-containing medium Directing the transfer of electrical energy from the Creates an effective surface area for electrical energy transfer for ablation of larger heart tissue Electrical energy through the porous material while transporting the electrical energy for A heart tissue resection device consisting of a controller that enables on-transport. 405. In addition, there is a conductive element that connects the generator and the medium in the interior area of the wall. And, during the second mode, the controller detects that the conductive material is While the ion transport of electric energy by the medium through the porous material An element indicating that electrical energy from the generator is to be transported, if possible. The device of claim 404, wherein the device is connected to a device. 406. A medium source containing ions; A generator of electrical energy, A processor that processes electrical phenomena in heart tissue; A wall with an outer surface surrounding the interior area, at least a portion of the wall A wall made of conductive material having a surface area for detecting electrical phenomena in tissue And a lumen for transporting the ion-containing medium from the liquid source to the interior region of the wall. And at least a part of the wall is shaped to be able to pass ions contained in the medium. A wall adjacent to the formed conductive material made of a porous material, A conductive element connecting the generator and the medium in the interior region of the wall; And a controller connected to the liquid source, generator and processor. The controller, in the first mode, for transport to the processor, Instruct the conductive material to detect electrical phenomena in the heart tissue and While the transfer of the ion-containing medium is instructed by the Directs the transfer of electrical energy from the generator, thereby causing the conductive material to Effective surface area for electrical energy transfer for ablation of heart tissue larger than surface area Electrical energy through the porous material while transporting electrical energy to form Heart tissue ablation device consisting of a controller that enables ion transport of ghee. 407. A porous material that is sized to block the passage of polymers The apparatus of claim 404 or 405 or 406. 408. 405. The device according to claim 401 or 406, wherein the porous material comprises an ultrafiltration membrane. Place. 409. 405. The device according to claim 401 or 406, wherein the porous material comprises a microporous membrane. Place. 410. 400. The conductive element is a conductive electrode in an interior region of the wall. Or the apparatus of 401 or 402 or 405 or 406. 411. 403. The conductive material of claim 400 or 401, wherein the conductive material comprises a coating applied to the wall. Or the apparatus of 402 or 405 or 406. 412. The conductive material is a foil attached to a wall. The device of 02 or 405 or 406. 413. The conductive material is a part of the wall that protrudes together. The device according to 402 or 405 or 406. 414. Conductive material must be free of uninsulated signal wires exposed outside the wall. Apparatus according to claim 400 or 401 or 402 or 405 or 406. 415. 400. The medium of claim 400 or 401 or 402 or 405 or 406. The apparatus according to 406. 416. 400. The medium of claim 400 or 401, wherein the resistance of the medium is about 150 Ωcm or less. The device according to 402 or 405 or 406. 417. 415. The apparatus of claim 416, wherein the resistance of the medium is no greater than about 10 ohm-cm. 418. 415. The apparatus of claim 416, wherein the medium has a resistance of about 5 ohm-cm or less. 419. The electric resistance of the porous material is about 500 Ω · cm or more. The device according to 401 or 402 or 405 or 406. 420. The electric resistance of the porous material is about 500 Ω · cm or less. The device according to 401 or 402 or 405 or 406. 421. 41. The porous material is hydrophilic, wherein the porous material is hydrophilic. 405. The apparatus according to 5 or 406. 422. A lumen transports the ion-containing medium to an interior area under internal pressure, and 400. The porous material of claim 400 or 401, wherein the porous material has a bubble point value greater than the internal pressure. The device according to 402 or 405 or 406. 423. The device of claim 422, wherein the porous material is hydrophilic. 424. A wall surrounding the interior area, At least part of the wall is connected to a source of electrical energy for transport of electrical energy. Made of conductive material that can be connected, And a lumen for transporting the media to an interior area capable of holding the ion-containing media. And At least a part of the conductive material is large enough to pass ions contained in the medium. An electrode assembly made of a porous material formed on the substrate. 425. Furthermore, it enables ion transport of electrical energy through porous materials Equipped with a conductive element that connects the electrical energy source with the medium in the interior area 425. The assembly of claim 424. 426. 43. The conductive element comprises a conductive electrode in an interior region of the wall. An assembly according to claim 5. 427. 425. The assembly of claim 426, wherein the conductive electrodes comprise a noble metal. 428. The conductive electrode is made of gold, platinum and platinum / iridium as essential components. 426. A material comprising a material selected from the group consisting of: The described assembly. 429. In addition, a conductive material is used to carry the detected electrical signal. 425. The assembly of claim 424 or 425, comprising an element connected to the. 430. A wall surrounding the interior area, at least a portion of which is electrically -A wall of conductive material connected to a source of electrical energy for transport, A lumen capable of transporting the medium into an interior region capable of holding the ion-containing medium; At least a part of the conductive material is large enough to pass ions contained in the medium. Consisting of a porous material formed in Then, it enables ion transport of electric energy by the medium through the porous material. Conductive elements that connect the medium in the interior area to the source of electrical energy Electrode assembly. 431. In addition, a conductive material is used to carry the detected electrical signal. 430. The assembly of claim 430, comprising an element connected to the. 432. 44. The conductive element comprises a conductive electrode in an interior region of the wall. Assembly according to claim 0. 433. 432. The assembly of claim 432, wherein the conductive electrode comprises a noble metal. 434. The conductive electrode is made of gold, platinum and platinum / iridium as essential components. 432. A material comprising a material selected from the group consisting of: The described assembly. 435. Claims in which the porous material is sized to block the passage of polymers 430. The assembly according to clause 430. 436. 430. The assembly of claim 430, wherein the porous material comprises an ultrafiltration membrane. 437. 430. The assembly of claim 430, wherein the porous material comprises a microporous membrane. 438. 430. The apparatus according to claim 423 or 430, wherein the medium comprises a hypertonic solution. 439. 423. The assembly of claim 423, wherein the hypertonic solution comprises sodium chloride. 440. 439. The method of claim 439, wherein the concentration of sodium chloride is at or near saturation. Mumburi. 441. 439. The composition of claim 439, wherein the concentration of sodium chloride is up to about 9% w / v. On-board assembly. 442. 439. The assembly of claim 436, wherein the hypertonic solution comprises potassium chloride. 443. 430. The medium of claim 1 or 430, wherein the medium has a resistance of about 150 ohm-cm or less. Assembly. 444. 423. The medium of claim 422 or 430, wherein the medium has a resistance of about 10 ohm-cm or less. On-board assembly. 445. 430. The method of claim 422 or 430, wherein the medium has a resistance of about 5 ohm-cm. Assembly. 446. 43. The medium comprises a material whose presence increases the viscosity of the medium. 430. The assembly according to 0 or 430. 447. The medium has at least one ion, the presence of which increases the viscosity of the medium. 430. The assembly of claim 422 or 430, wherein the assembly comprises a conductive material. 448. The at least one ionic material comprises a radiopaque material. The assembly of 447. 449. The medium contains a non-ionic material whose presence increases the viscosity of the medium The assembly of claim 422 or 430. 450. 449. The assembly of claim 449, wherein the non-ionic material comprises glycerol. - 451. 449. The assembly of claim 448, wherein the non-ionic material comprises mannitol. . 452. 422. The electrical resistance of the porous material is about 500 Ω · cm or more. Is the assembly according to 430. 453. 422. The electric resistance of the porous material is about 500 Ω · cm or less. Is the assembly according to 430. 454. In addition, assembled within the interior area to form a support structure under the wall 430. The assembly of claim 422 or 430, wherein the assembly comprises a provided member. 455. The assembly of claim 454, wherein the solid support member comprises a metallic material. 456. 454. The assembly of claim 454, wherein the metallic material comprises nickel titanium. 457. 454. The assembly of claim 454, wherein the metallic material comprises stainless steel. 458. 454. The assembly of claim 454, wherein the solid support member comprises a plastic material. Brie. 459. The solid support members are assembled such that they are in a circumferentially spaced relationship. 454. The assemblage of claim 454, comprising a raised and extended spline element. Lee. 460. 454. The assembly of claim 454, wherein the solid support member comprises a porous foam. - 461. 430. The assembly according to claim 422 or 430, wherein the porous material is hydrophilic. Lee. 462. The lumen carries the ion-containing medium to an interior area under internal pressure. 422. The porous material having a bubble point value greater than its internal pressure. Is the assembly according to 430. 463. An assembly according to claim 1, wherein the porous material is hydrophilic. 464. An ion-containing medium source; A generator of electrical energy, A wall with an outer surface surrounding the interior area, at least a portion of which is electrically A wall made of a conductive material connected to an electrical energy source for energy transfer An electrode comprising a lumen for transporting the ion-containing medium to the interior region; And at least a part of the conductive material is capable of passing ions contained in the medium. Made of porous material formed in size, Then, an instruction is given to transfer energy from the generator by the conductive material. On the other hand, by instructing the transport of the ion-containing medium from the medium source, the necessary tissue heating can be performed. A controller connected to the media source and generator to obtain the effect While porous materials carry electrical energy, ions can be transported through porous materials. A living tissue heating device consisting of a controller that can function. 465. In addition, there is a conductive element that connects the generator and the medium in the interior area of the wall. And while the conductive material is carrying electrical energy, The electrical energy from the generator is used to enable the ion transport of electrical energy by the medium. An element is sent to the controller to direct the transfer of energy to the element. The device of claim 464 wherein the devices are connected. 466. An ion-containing medium source; A generator of electrical energy, A wall with an outer surface surrounding the interior area, at least a portion of which is electrically A wall made of a conductive material connected to an electrical energy source for energy transfer An electrode comprising a lumen for transporting the ion-containing medium to the interior region; And at least a part of the conductive material is capable of passing ions contained in the medium. Made of porous material formed in size, A conductive element connecting the generator and the medium in the interior region of the wall; Then, an instruction is given to transfer energy from the generator by the conductive material. On the other hand, by instructing the transport of the ion-containing medium from the medium source, the necessary tissue heating can be performed. A controller connected to the media and generator to obtain the effect Allows transport of ions through porous material while material carries electrical energy A heating device for living tissue, comprising: a controller; 467. The controller achieves the desired tissue heating effect by removing the living tissue. 475. The apparatus of claim 464 or 465 or 466, which is effective for configuration. 468. The controller achieves the desired tissue heating effect by removing the heart tissue 475. The apparatus of claim 464 or 465 or 466, which is effective for configuration. 469. An ion-containing medium source; A generator of electrical energy, A processor for processing electrical signals in the heart tissue; and A wall with an outer surface surrounding the interior area, at least a portion of which is electrically A wall made of a conductive material connected to an electrical energy source for energy transfer An electrode comprising a lumen for transporting the ion-containing medium to the interior region; And at least a part of the conductive material is capable of passing ions contained in the medium. Made of porous material formed in size, Then, an instruction is given to transfer energy from the generator by the conductive material. On the other hand, by instructing the transport of the ion-containing medium from the medium source, the necessary tissue heating can be performed. A controller connected to the media source and generator to obtain the effect While porous materials carry electrical energy, ions can be transported through porous materials. A biological tissue resection device consisting of a controller that can function. 470. In addition, there is a conductive element that connects the generator and the medium in the interior area of the wall. And, during the second mode, the conductive material carries electrical energy while To enable ion transport of electrical energy by the medium through the porous material, The controller sends an element to direct the transfer of electrical energy from the creature. 469. The device of claim 469, connected to the 471. An ion-containing medium source; A generator of electrical energy, A processor for processing electrical signals in the heart tissue; and A wall with an outer surface surrounding the interior area, at least a portion of which is electrically A wall made of a conductive material connected to an electrical energy source for energy transfer An electrode comprising a lumen for transporting the ion-containing medium to the interior region; And at least a part of the conductive material is capable of passing ions contained in the medium. Made of porous material formed in size, A conductive element connecting the generator and the medium in the interior region of the wall; Then, an instruction is given to transfer energy from the generator by the conductive material. On the other hand, by instructing the transport of the ion-containing medium from the medium source, the necessary tissue heating is performed. A controller connected to the media source and generator to obtain the effect While porous materials carry electrical energy, ions can be transported through porous materials. A biological tissue resection device consisting of a controller that can function. 472. A porous material that is sized to block the passage of polymers 48. The apparatus according to claim 466 or 471. 473. 471. The device according to claim 466 or 471, wherein the porous material comprises an ultrafiltration membrane. Place. 474. 471. The device according to claim 466 or 471, wherein the porous material comprises a microporous membrane. Place. 475. 468. The conductive element is a conductive electrode in the interior region of the wall. Or the apparatus of 469 or 470 or 471. 476. 466 or 467 or 468 or 469 or the medium comprises a hypertonic solution. The device according to 470 or 471. 477. 466. 467 or 467, wherein the resistance of the medium is no greater than about 150 ohm-cm. 468 or 469 or 470 or 471. 478. The device of claim 477, wherein the resistance of the medium is less than or equal to about 10 ohm-cm. 479. The device of claim 477, wherein the resistance of the medium is about 5 ohm-cm. 480. 466. The porous material has an electrical resistance of at least about 500 Ω · cm. 467 or 468 or 469 or 470 or 471. 481. 466. The porous material has an electrical resistance of about 500 Ω · cm or less. 467 or 468 or 469 or 470 or 471. 482. 466 or 467 or 468 or 46 wherein the porous material is hydrophilic. 49. The apparatus according to 9 or 470 or 471. 483. A lumen transports the ion-containing medium to an interior area under internal pressure, and 466 or 467 or a porous material having a bubble point value greater than the internal pressure. 468 or 469 or 470 or 471. 484. The device of claim 483, wherein the porous material is hydrophilic. 485. An outer wall surrounding the inner area and tightly attached to the tissue; A lumen for transporting the containing medium to the interior region and at least a portion of the wall is contained in the medium; Made of porous material sized to allow the ions to pass through An electrode comprising a conductive element in contact with the medium in the area; Conductive air to transport ions to the tissue through the media and porous material Element connected to a conductive element that carries the electrical ablation energy A generator of electrical ablation energy; At least one sensing element held on the outer electrode wall for sensing temperature; , At least partially, the temperature sensed by the at least one sensing element To control the delivery of electroablation energy to the conductive element based on A generator and a controller to which at least one sensing element is connected. Biological tissue resection device. 486. At least the temperature sensed by the at least one sensing element Configured electrical ablation energy delivered to conductive elements based in part 485. The apparatus of claim 485, wherein the controller defines the output value of the energy. 487. Controller transfers electrical ablation energy to conductive elements 490. The device of claim 485, wherein the duty cycle is defined. 488. The controller outputs the electrical ablation energy with a pulse output to the conductive element. 490. The device of claim 486, wherein the device communicates to a client. 489. While the electrodes ionically carry the ablation energy, 486. The controller according to claim 486, wherein the set maximum temperature condition detected by the controller is specified. On-board equipment. 490. The controller periodically detects by at least one sensing element. Compare the known temperature with the target maximum temperature condition and at least partially For limiting the transfer of electrical ablation energy to a conductive element based on a comparison 490. The device of claim 489, wherein 491. The controller determines the desired therapeutic effect, including at least the target lesion depth. 490. Apparatus according to claim 485 or 486, comprising an element for inputting results. 492. While the electrodes ionically carry the ablation energy, Operating conditions based on the desired therapeutic effect, including determination of the target maximum temperature to be sensed 50. The apparatus of claim 491, wherein the controller comprises the defining processing means. 493. Controller detected by at least one sensing element Compare the temperature with the target maximum temperature condition and at least partially To issue instructions to limit the transfer of electrical ablation energy to the conductive element 492. The apparatus of claim 492. 494. The controller defines a target electrical resistance of the porous material of the outer wall. 485 or 486. 495. 498. The device of claim 494, wherein the target electrical resistance is greater than or equal to about 500 ohm-cm. . 496. 498. The device of claim 494, wherein the target electrical resistance is no greater than about 500 ohm-cm. . 497. 485. The controller of claim 485 or claim 4 wherein the controller defines a target electrical resistance of the media. 86. The apparatus according to 86. 498. 499. The target electrical resistance of the medium is no greater than about 150 ohm-cm. Equipment. 499. 497. The apparatus of claim 497, wherein the target electrical resistance of the medium is about 5 ohm-cm. 500. A controller controls the rate of liquid perfusion of the medium through the porous material. 500. The apparatus according to claim 485 or 486. 501. Controller determines based at least on physiological fluid overload 500. The apparatus of claim 500, comprising means for maintaining a liquid perfusion rate below a set maximum. Place. 502. The controller uses the liquid to determine, at least in part, the perfusion rate. The apparatus of claim 500, wherein the apparatus defines a viscosity of the medium. 503. A controller is positioned close to where the outer wall is in contact with the tissue 485. The apparatus according to claim 485 or 486, further comprising detecting means for detecting the impedance. Equipment. 504. The controller sets the impedance detected by the detection means to the minimum value. 50. A method for controlling the perfusion rate of a liquid medium through a porous material to maintain 3. The device according to 3. 505. A controller senses the rate of perfusion of the liquid medium through the porous material Stipulates that the impedance detected by The device of claim 503. 506. 485. The method of claim 485, wherein the electrical ablation energy comprises radio frequency energy. Is the device of 486. 507. 490. The device of claim 485 or 486, wherein the porous material comprises an ultrafiltration membrane. Place. 508. 507. The controller defines a target electrical resistance for the ultrafiltration membrane. The described device. 509. 509. The device of claim 508, wherein the target electrical resistance is greater than or equal to about 500 ohm-cm. . 510. 509. The device of claim 508, wherein the target electrical resistance is no greater than about 500 ohm-cm. . 511. 485. The device according to claim 485 or 486, wherein the porous material comprises a microporous membrane. Place. 512. 511. The controller defines a target electrical resistance of the microporous membrane. The described device. 513. 512. The device of claim 512, wherein the target electrical resistance is greater than or equal to about 500 ohm-cm. . 514. 512. The device of claim 512, wherein the target electrical resistance is no greater than about 500 ohm-cm. . 515. The controller adjusts the internal pressure of the internal area below the value of the bubble point of the porous material. The device of claim 485 or 486 as defined below. 516. A wall surrounding the interior area and in contact with the tissue and transporting the ion-containing medium to the interior area Lumens and their walls are large enough to allow the ions contained in the medium to pass through. A first and a second region made of a porous material formed and arranged separately, Electrical media for transporting ions to the tissue through the medium and the first and second porous regions; Electrical ablation energy coupled to the medium in the interior region of the electrode carrying the ablation energy A generator of lugies, The temperature is held on the wall in proximity to the first and second porous regions, respectively, for sensing temperature. First and second sensing elements, Based at least in part on the temperature sensed by the first and second sensing elements , A generator and first and second to control the delivery of electroablation energy to the medium. Biological tissue resection device comprising a controller connected to two detection elements . 517. The controller is detected by at least one detection element Target electroablation energy delivered to the medium based at least in part on temperature The device of claim 516, wherein the output value is determined. 518. The controller detects the temperature detected by the first and second sensing elements Electrical ablation through the first and second porous regions based at least in part on 517. The device of claim 516, wherein the device defines a duty cycle of energy ion transport. 519. A controller controls the electrical ablation energy through the first and second porous regions. 517. The apparatus of claim 517, wherein the energy is transmitted by ion transport. 520. While the electrodes are ionically delivering the ablation energy, the controller 6. The target maximum temperature detected by the first and second detection elements is defined. The apparatus according to claim 16, 521. The controller detects the temperature detected by the first and second sensing elements And target maximum temperature conditions periodically and at least partially based on the comparison. 6. An instruction to limit ion transport through the first and second porous regions. 20. The apparatus according to 20. 522. The controller determines the desired treatment result, including at least the target lesion depth. The device of claim 520, comprising an element for inputting the result. 523. While the electrode ionically delivers the ablation energy, the target maximum temperature Desirable treatment result including determining by detection by the first and second sensing elements 522. The controller comprising processing means for defining operating conditions based on The described device. 524. The controller periodically detects by at least one sensing element. Compare the known temperature with the target maximum temperature condition and at least partially For limiting the transfer of electrical ablation energy to a conductive element based on a comparison 523. The device of claim 523, wherein 525. 53. The at least one region of porous material comprises an ultrafiltration membrane. 3. The apparatus according to 2. 526. 53. The at least one region of porous material comprises a microporous membrane. 3. The apparatus according to 2. 527. The controller adjusts the internal pressure of the internal area below the value of the bubble point of the porous material. The device of claim 516, as defined below.