JP2003533243A - 腹膜透析治療をモニタリングおよび制御するための方法および装置 - Google Patents
腹膜透析治療をモニタリングおよび制御するための方法および装置Info
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- JP2003533243A JP2003533243A JP2001557617A JP2001557617A JP2003533243A JP 2003533243 A JP2003533243 A JP 2003533243A JP 2001557617 A JP2001557617 A JP 2001557617A JP 2001557617 A JP2001557617 A JP 2001557617A JP 2003533243 A JP2003533243 A JP 2003533243A
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- dialysate
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
- A61M1/14—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis
- A61M1/28—Peritoneal dialysis ; Other peritoneal treatment, e.g. oxygenation
- A61M1/282—Operational modes
-
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- A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
- A61M1/14—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis
- A61M1/15—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis with a cassette forming partially or totally the flow circuit for the treating fluid, e.g. the dialysate fluid circuit or the treating gas circuit
- A61M1/154—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis with a cassette forming partially or totally the flow circuit for the treating fluid, e.g. the dialysate fluid circuit or the treating gas circuit with sensing means or components thereof
-
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- A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
- A61M1/14—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis
- A61M1/15—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis with a cassette forming partially or totally the flow circuit for the treating fluid, e.g. the dialysate fluid circuit or the treating gas circuit
- A61M1/155—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis with a cassette forming partially or totally the flow circuit for the treating fluid, e.g. the dialysate fluid circuit or the treating gas circuit with treatment-fluid pumping means or components thereof
-
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- A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
- A61M1/14—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis
- A61M1/15—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis with a cassette forming partially or totally the flow circuit for the treating fluid, e.g. the dialysate fluid circuit or the treating gas circuit
- A61M1/159—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis with a cassette forming partially or totally the flow circuit for the treating fluid, e.g. the dialysate fluid circuit or the treating gas circuit specially adapted for peritoneal dialysis
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
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- A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
- A61M1/14—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis
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- A61M1/281—Instillation other than by gravity
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
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- A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
- A61M1/14—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis
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- A61M1/285—Catheters therefor
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61M—DEVICES FOR INTRODUCING MEDIA INTO, OR ONTO, THE BODY; DEVICES FOR TRANSDUCING BODY MEDIA OR FOR TAKING MEDIA FROM THE BODY; DEVICES FOR PRODUCING OR ENDING SLEEP OR STUPOR
- A61M5/00—Devices for bringing media into the body in a subcutaneous, intra-vascular or intramuscular way; Accessories therefor, e.g. filling or cleaning devices, arm-rests
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- A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
- A61M1/14—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis
- A61M1/15—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis with a cassette forming partially or totally the flow circuit for the treating fluid, e.g. the dialysate fluid circuit or the treating gas circuit
- A61M1/156—Constructional details of the cassette, e.g. specific details on material or shape
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- A—HUMAN NECESSITIES
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- A61M1/00—Suction or pumping devices for medical purposes; Devices for carrying-off, for treatment of, or for carrying-over, body-liquids; Drainage systems
- A61M1/14—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis
- A61M1/15—Dialysis systems; Artificial kidneys; Blood oxygenators ; Reciprocating systems for treatment of body fluids, e.g. single needle systems for hemofiltration or pheresis with a cassette forming partially or totally the flow circuit for the treating fluid, e.g. the dialysate fluid circuit or the treating gas circuit
- A61M1/156—Constructional details of the cassette, e.g. specific details on material or shape
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- A61M2205/00—General characteristics of the apparatus
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Abstract
Description
腹膜透析の性能をモニタリングするための方法および装置に関する。
ために透析を使用することは、公知である。2つの主要な透析方法が使用される
:血液透析;および腹膜透析。
の膜は、血液を浄化するための人工腎臓として機能する。それは、特別な機器を
必要とする体外処置であるので、特定の固有の欠点が、血液透析には存在する。
は、患者自身の腹膜を半透膜として利用する。この腹膜は、身体の腹腔の膜状層
である。良好な灌流に起因して、この腹膜は、天然の半透膜として機能し得る。
析溶液または透析液と呼ばれる。拡散および浸透圧交換は、天然の身体膜を横切
って、溶液と血流の間で起こる。これらの交換は、腎臓が通常排出する老廃生成
物を除去する。この老廃生成物は、代表的に、尿素およびクレアチニンのような
溶質からなる。腎臓はまた、透析によって調節される必要のあるナトリウムおよ
び水のような他の物質のレベルを維持する。透析の間に腹膜を横切る水および溶
質の拡散は、限外濾過と呼ばれる。
に導入される。透析液と血液との間の溶質の交換は、拡散によって達成される。
さらなる除去は、血液から透析液への適切な浸透圧勾配を提供して、水が血液か
ら流出することを可能にすることによって達成される。このことは、適切な酸−
塩基バランス、電解質バランスおよび流体バランスが、身体内で達成されること
を可能にする。この透析溶液は、単に、カテーテルを通して体腔から排液される
。
、従って血液透析に比較しての透析時間の持続時間の増加;および自動装置が使
用された場合の費用の増加。
動腹膜透析(「APD」)である。APDは、機器(サイクラーと呼ばれる)を
使用して、患者の腹腔におよび腹腔から、腹膜透析溶液を、自動注入、休止、お
よび排液する。APDは、特に、腹膜透析患者に対して魅力的である。なぜなら
、これは、患者が寝ている間の夜に実施され得るからである。このことは、患者
を、彼/彼女の起きている時間および仕事の時間の間の移動性の連続的な腹膜透
析の日々の要求から自由にする。
を腹腔から空にするための初期排液サイクルで始まる。次いで、このAPD手順
は、順番に続く充填、休止および排液の段階の連続を通して進行する。各充填/
休止/排液手順は、サイクルと呼ばれる。APDは、多くの異なる方法で実施さ
れ得、そして実施される。
現在のシステムは、単に、患者カテーテルに取り付けられたラインまたは管腔に
ポンプが適用し得る外圧(または吸引)を制限するのみである。患者がシステム
(しばしば、サイクラーと呼ばれる)の下に置かれる場合、重力頭が、サイクラ
ーが患者カテーテルに適用し得る正の充填圧を加える。逆に、この患者がサイク
ラーの上に位置する場合、重力頭は、サイクラーが患者カテーテルに適用し得る
正の充填圧から減少する。
、サイクルの間に患者を完全には引かないからである。具体的に、現在利用可能
なサイクラーは、患者がいくらかの流体を吸収したか否かまたはいくらかの流体
が、単に、患者またはカテーテルの位置のために、排液され得ないか否かを決定
することができない。
達されるべきである流体の量を決定するために、最小排液閾値を利用する。例え
ば、サイクラーが患者が「空」であると決定したときに、充填容量の85%が排
液されていた場合、次の充填容量は100%となる。80%のみが排液される場
合、次の充填容量は95%に制限される。
が鳴る。この所定の割合は、代表的に、充填容量の50%または100%のいず
れかであり得る。しかし、患者は、彼/彼女が満たされ過ぎたように感じない場
合、この警報を無効にすることができる。1回の治療の間に患者がuF警報を無
効にし得る回数は、サイクラーのソフトウェアによって制限され得る。しかし、
このuF警報は、代表的に、透析液と共に腹腔にまた蓄積され得る実際の限外濾
過液を考慮はしない。
た容量にまで患者を満たす。医師は、この充填容量を、患者の大きさ、体重およ
び他の因子に基づいて処方する。しかし、現在利用可能なサイクラーは、腹腔内
圧をモニターできないので、医師は、処方を実施する場合、この因子を考慮する
ことができない。腹腔内圧(IPP)は、限外濾過(UF)に対する効果を有す
ることがまた知れらている。
ずれも、腹腔内圧をモニターすることを試みない。
れ、患者12および排液容器13が概略的に図示される。容器11から患者12
への透析液の注入は、14によって示される重力頭によって引き起こされるが、
一方で、患者12から排液容器13への使用された透析液の排液が、15によっ
て示される排液頭によって引き起こされる。このサイクラー10aは、患者12
の腹膜の内部の圧力をモニターするためのセンサを含まない。単一管腔16は、
透析液容器11と排液容器13の両方を患者12に接続する。サイクラー10a
によって作動される弁17、18は、容器11から患者12への透析液の流れま
たは患者12から排液容器13への廃棄物質の流れのいずれかを制御する。
11は、加圧チャンバ19内に収容される。このチャンバ19は、患者を充填ま
たは排液するために加圧または排液され得る。再び、弁17、18のこの選択的
作動は、透析液が、患者12に移動されているかまたは患者12から移動されて
いるかを制御する。再び、患者12の腹腔内圧を検出またはモニタするためのセ
ンサは提供されない。
接続され、順に、透析液容器11を共通管腔またはカテーテル16(これらは、
患者に接続される)に接続する。流体フロー制御弁が23に提供され、そしてサ
イクラー10cによって制御される。排液容器13がまた、ポンプ24に接続さ
れ、このポンプ24は、次いで、排液容器13を管腔16に接続する。制御弁が
また25に提供される。
患者ライン16に適用される重力頭(図1を参照のこと)あるいは吸引または圧
力(図2および3を参照のこと)によって決定される。代表的に、これらのサイ
クラー10a〜10cは、充填速度または排液速度のいずれをも最適化すること
ができない。なぜなら、圧力は、重力頭あるいは図2のチャンバ10bによって
適用される圧力または吸引(これらは、患者ライン16の対向端部で起こる)の
いずれかによって固定されるからである。従って、腹腔内圧を測定することなく
または腹腔内圧を評価する方法を有することなく、排液速度または充填速度のい
ずれかを最適化することは困難である。図3のサイクラー10cの場合において
、排液速度または充填速度を最適化することは、いかなる圧力の読み取りをも全
く欠くので推定である。
)に、患者の腹腔内圧を測定する改善されたサイクラーに対する必要性が存在す
る。さらに、腹腔内圧を測定し、そしてサイクルの間に患者をより完全に排液す
るためのそのデータを使用する改善されたサイクラーに対する必要性が存在する
。さらに、患者を過剰充填することを回避するために腹腔内圧を正確に測定する
改善されたサイクラーに対する必要性が存在する。最後に、充填サイクルおよび
排液サイクルの両方の間に、腹腔内圧をモニタして、患者が充填および排液され
る速度を最適化し、従って、治療期間の休止部分を増加させる改善されたサイク
ラーに対する必要性が存在する。
するためのシステムを提供することによって上記の必要性を満たし、この透析液
容器は、その間にインラインで接続される第一の圧力センサと共に患者に接続さ
れ、そしてこの排液容器は、その間にインラインで接続される第二の圧力センサ
と共に患者に接続される。
センサとの間にインラインで配置される第一のポンプを備える。
ead)下で、透析液容器から患者に流れる。
間にインラインで配置される。
る。
、一方で、透析液は、透析液容器から患者に流れる。
で、透析液は、患者から排液容器に流れる。
サに接続しそしてこの第一のセンサをカテーテルに接続する第一の管腔および排
液容器を第二のセンサに接続し、そしてこの第二のセンサをカテーテルに接続す
る第二の管腔を備え、このカテーテルは、患者に接続され、患者から排液容器へ
の透析液の流れが、第一の管腔から透析液を排液し、そして透析液を第一の管腔
から、第二の管腔を通って排液容器に流させる。
真空センサである。
の方法は、以下の工程を包含する:患者の腹膜にカテーテルを配置する工程:少
なくとも1つの透析液容器を提供する工程;この透析液容器を、第一の管腔を用
いてカテーテルに接続する工程であって、この第一の管腔は、インラインでカテ
ーテルと透析容器との間に配置される第一の圧力センサを備える、工程;少なく
とも1つの排液容器を提供する工程;この排液容器を第二の管腔を用いてカテー
テルに接続する工程であって、この第二の管腔は、インラインでカテーテルと排
液容器との間に配置される第二の圧力センサを備える工程;透析液容器から患者
の腹膜へと透析液を移動させ、そして第二の圧力センサを用いて患者の腹腔内圧
をモニタする工程;ならびに患者の腹膜から排液容器に透析液を移動させ、患者
の第一の腹腔内圧を第一の圧力センサを用いてモニタする工程。
工程は、さらに、透析液容器と第一の圧力センサとの間にインラインで配置され
た第一のポンプを用いて透析液容器から患者に透析液をポンピングする工程を包
含する。
は、さらに、排液容器と第二の圧力センサとの間にインラインで配置された第二
のポンプを用いて、患者の腹膜から排液容器に透析液をポンピングする工程を包
含する。
て透析液容器から患者の腹膜に透析液を移動させる工程が、さらに、静水圧頭下
で、透析液容器から患者に透析液を流す工程を包含する。
者の腹膜から排液容器に透析液を移動させる工程が、さらに、静水圧頭下で患者
の腹膜から排液容器へと透析液を流す工程を包含する。
囲を読み、そして添付の図面を参照して明らかとなる。
ばしば、図形、想像線、線図および断片図によって示されることが理解されるべ
きである。特定の例において、本発明の理解のために必要でないかまたは他の詳
細を認知することを困難にする詳細は、省略され得る。もちろん、本発明は、本
明細書中に例示される特定の実施形態に必ずしも制限されないことが理解される
べきである。
を備える。このポンプ31は、圧力センサ32に接続される。このポンプ31お
よび圧力センサ32は、透析液容器11をカテーテル34に接続する管腔33に
インラインで配置される。制御弁が35、36に提供される。排液容器13はま
た、センサ37に接続されるポンプ36に接続される。ポンプ36およびセンサ
37はまた、排液容器13をカテーテル34に接続する管腔38にインラインで
接続される。制御弁が、再び、41、42に提供される。充填の間、ポンプ31
は、容器11から管腔31およびカテーテル34を介して、患者12の腹膜(示
されず)に透析液をポンピングする。この時間の間、センサ37は、腹腔内圧を
モニタしそして測定する。信号が、43で概略的に示されるサイクラー30の制
御器に送られる。制御パネルは、一般に44で示される。
る。図4に示される実施形態において、センサ32と患者12との間には、ポン
プまたは制御弁は配置されない。
に配置されるセンサ53、54を有する可逆ポンピングチャンバ51、52を備
えるサイクラー50が示される。制御弁55および56は、可逆ポンピングチャ
ンバ51とセンサ53の別の側面に配置され、そして制御弁57、58が、可逆
ポンピングチャンバ52とセンサ54のいずれかの側面に提供される。これらの
センサ53、54は、可逆ポンピングチャンバ51、52の隔膜に対する圧力を
実質的に測定する。
液容器13を収容するチャンバ61および透析液容器11を収容するチャンバ6
2を備える。各チャンバ61、62は、63、64で示される、一体化された弁
アセンブリおよび圧力センサを備える。図6に示される実施形態60において、
チャンバ61は、排液され得なければならない。透析液は、重力または圧力充填
によって、透析液容器11から流れ得る。再度、弁アセンブリ/センサの組み合
わせ63、64が、上で議論されたように、患者12の腹腔内圧をモニタリング
する。
両方が、一体化された制御弁および圧力センサ71、72に接続される。一体化
された制御弁および圧力センサ71、72の各々が、それぞれ管腔73、74に
接続され、これらの管腔は、Y型接続によってカテーテル75aに接続される。
Y型接続およびクランプの全ての詳細は示されないが、当業者に公知である。透
析液容器11から患者への流れは、75に示される重力頭のもとで行われ、一方
で患者から排液容器13への流れは、76に示される重力頭のもとで行われる。
80を示す。二重充填セル81、82が、ライン84、85によって接続される
減圧によって、可撓性圧力感知膜83に接続される。サイクラーを患者に接続す
る管腔が、86で示される。
ャンバカセットは、カセット87を患者に接続する出力ライン88および患者を
カセット87に接続する入力ライン89を備える。ライン90は、カセット87
を透析液容器(図示せず)に接続する。各ポンピングチャンバ91、92は、3
つ全てのライン88、89および90と連絡する。従って、全てのラインが、ポ
ンピングチャンバ91、92のいずれかと接続され得る。ポンピングチャンバ9
1、92は、93に示される共通の隔膜によって、片側が接続される。流れは、
94、95、96および97に示される隔膜弁の使用によって、制御される。圧
力センサは、120、121、122、123、124、125に示される。し
かし、圧力センサ123および120は、本発明によって腹腔内圧を測定するた
めに使用されるセンサである。残りのセンサ121、122、124、125は
、ポンプ126、127の作動をモニタリングするために使用される。
ライン89を介して腹腔内圧を測定し得る。左の隔膜ポンプ126がライン89
を通して患者から流体を排液している場合には、センサ120は、ライン88を
介して腹腔内圧を測定し得、一方で右のポンプ27は、128で概略的に示され
る排液ラインを通して、排液容器(図示せず)に流体をポンピングする。右の隔
膜ポンプ127が、患者から流体を排液するために使用されている場合には、セ
ンサ120が腹腔内圧を測定し得、一方で左の隔膜ポンプ126は、129で概
略的に示される排液ラインを通して排液容器(図示せず)に流体をポンピングす
る。
100を示す。二重管腔カテーテル100の使用は、二重管腔患者ラインと比較
して、圧力が測定される点を、別個の流路101、102を通る連絡によって、
腹膜自体の内部に移動させ得る。二重管腔カテーテル100は、単一管腔カテー
テルと同様に取り付けられるが、フロースルーカテーテルまたは標準的なカテー
テルのいずれかとして機能する。両方の流路101、102は、排液および充填
の間に、流体を引き抜きそして送達するために使用される。一方の流路が流体を
送達する間に、他方の流路は排液する。一般的に103で示される端部セクショ
ンは、穿孔されている。
たものとの比較は、以下のように要約される:
30頃に患者を目覚めさせたことを示す。患者は、この警報を無視した。なぜな
らこの患者は、満たされ過ぎたことを感じず、そしてすぐに眠りに戻ったからで
ある。この患者は、呼吸が困難であり過剰に満たされ過ぎたことを感じたときで
ある、約15分後に目覚めた。この患者は、手動で約1500mlを排液したが
、眠りに戻り得なかった。この患者は、製造業者に、形式的な製品の苦情を提出
した。
リアランス(夜間の患者の容量の合計に基づいて計算した)が、本発明の方法を
用いるサイクラーを使用してサイクラー3によって得られるクリアランスの84
.5%のみであったことを示す。
量が、患者の腹腔内圧による4つの場合ではなく、最大の充填容量による1つの
場合に、制限されたことを示す。この患者は、いかなる不快をも決して感じず、
そして夜の間に警報を出されなかった。IPPの制限は、完了していない連続的
な排液を有する場合でさえも、この患者の満たされ過ぎを防止する。この患者の
腹膜内の流体の容量は、決して3リットルを超えない。
る腹腔内圧を有した。この患者の呼吸は損なわれ得、そしてこの患者の心臓はよ
り激しく働かなければならないが、この不快は、休止5の間に4,099mlの
ピークとなるまで、この患者を熟睡から目覚めさせるには十分ではなかった。
ンスを提供し、一方で不快および生体身体器官の機能の抑制をもたらす満たされ
過ぎを防止する。負のuF警報は、めったに起こらない。なぜなら、必要な大き
さの満たされ過ぎが、IPPセンサによって防止されるからである。
存を使用して計算し得る: Δ(1/2ρV2+P−ρagh)+摩擦損失=0 患者ラインを通る流体の速度Vは、その流体密度と同様に、このラインの両端に
おいて同じであるので、この式は、以下のように書かれ得る: (P2−P1)−ρag(h2−h1)+摩擦損失=0 これは、以下のように並べ替えられ得る:
場合) ここで、 ag=981cm/秒2 ρ=1グラム/cm3
場合) ここで、 ag=981cm/秒2 ρ=1グラム/cm3
の任意の変化は、患者の睡眠時からの腹腔内圧(IPP)の増加に起因し得る。
クラーのための透析液中の尿素濃度111との間の濃度勾配が、グラフで示され
ている。図13および14に示す結果を比較すると、本発明のセンサを備えるA
PDサイクラーの方が優れた結果を与えることが明らかである。具体的には、図
13にグラフで示されるデータは、先行技術のAPDサイクラーを使用して得ら
れた。図14に得られるデータは、腹腔内圧をモニタリングするために2つのセ
ンサを利用するAPDサイクラーを使用して得られた。血流中の尿素濃度110
は、図13より図14においての方が低いことに注目のこと。透析液容量または
充填容量は、図13に示す治療より図14に示す治療に対して、より低いことに
さらに注目のこと。従って、本発明は、より低い充填容量での改善された尿素ク
リアランスを提供する。
変が、当業者に明らかであることが、理解されるべきである。このような変化お
よび改変は、本発明の意図および範囲から逸脱することなく、そしてその付随す
る利点を減少させることなく、なされ得る。従って、このような変化および改変
が、添付の特許請求の範囲に包含されることが、意図される。
を概略的に示す。
を概略的に示す。
を概略的に示す。
を組込んだ第五の実施形態を示す。
度をグラフ的に示す。
の血流中での尿素の濃度 対 透析液溶液中の尿素の濃度をグラフ的に示す。
流中の尿素の濃度 対 透析液中での尿素の濃度をグラフ的に示す。
Claims (21)
- 【請求項1】 患者に腹膜透析を提供するためのシステムであって、該シス
テムは、以下: 間に第一の圧力センサをインラインで接続して、患者に接続される透析液容器
;および 間に第二の圧力センサをインラインで接続して、該患者に接続される排液容器
、 を備える、システム。 - 【請求項2】 前記透析液容器と前記第一の圧力センサとの間にインライン
で配置される第一のポンプをさらに備える、請求項1に記載のシステム。 - 【請求項3】 静水圧頭のもとで、透析液が前記透析液容器から前記患者へ
と流れる、請求項1に記載のシステム。 - 【請求項4】 前記排液容器と前記第二の圧力センサとの間にインラインで
配置される第二のポンプをさらに備える、請求項1に記載のシステム。 - 【請求項5】 透析液が、静水圧頭のもとで前記患者から前記排液容器へと
流れる、請求項1に記載のシステム。 - 【請求項6】 透析液が前記透析液容器から前記患者へと流れる間に、前記
第二の圧力センサが、該患者の腹腔内圧を測定する、請求項1に記載のシステム
。 - 【請求項7】 透析液が前記患者から前記排液容器へと流れる間に、前記第
一の圧力センサが該患者の腹腔内圧を測定する、請求項1に記載のシステム。 - 【請求項8】 前記透析液容器を前記第一のセンサへ、そして該第一のセン
サをカテーテルへと接続する、第一の管腔、および 前記排液容器を前記第二のセンサへ、そして該第二のセンサを該カテーテルへ
と接続する、第二の管腔、 をさらに備え、 該カテーテルが、前記患者に接続されており、 該患者から該排液容器への透析液の流れが、透析液を該第一の管腔から排出し
、そして該第一の管腔からの該透析液を、該第二の管腔を通して該排液容器へと
流す、請求項1に記載のシステム。 - 【請求項9】 前記カテーテルが二重管腔カテーテルである、請求項8に記
載のシステム。 - 【請求項10】 前記第一および第二のセンサが、二重インライン圧力/減
圧センサである、請求項1に記載のシステム。 - 【請求項11】 患者に腹膜透析を提供するためのシステムであって、該シ
ステムが、以下: 間に第一のポンプおよび第一の圧力センサをインラインで接続して、該患者に
接続される透析液容器であって、該第一のセンサが、該第一のポンプと該患者と
の間に配置される、透析液容器、および 間に第二のポンプおよび第二の圧力センサをインラインで接続して、該患者に
接続される排液容器であって、該第二のセンサが、該第二のポンプと該患者との
間に配置される、排液容器、 を備える、システム。 - 【請求項12】 透析液が前記第一のポンプによって前記透析液容器から前
記患者へとポンピングされる間に、前記第二の圧力センサが、該患者の腹腔内圧
を測定する、請求項11に記載のシステム。 - 【請求項13】 透析液が前記第二のポンプによって前記患者から前記排
液容器へとポンピングされる間に、前記第一の圧力センサが、該患者の腹腔内圧
を測定する、請求項11に記載のシステム。 - 【請求項14】 前記透析液容器を前記第一のポンプへ、そして該第一のポ
ンプを前記第一のセンサへ、そして該第一のセンサをカテーテルへと接続する、
第一の管腔、および 前記排液容器を前記第二のポンプへ、そして該第二のポンプを前記第二のセン
サへ、そして該第二のセンサを該カテーテルへと接続する、第二の管腔、 をさらに備え、 該カテーテルが、該患者に接続されており、 該第二のポンプの作動が、透析液を該第一の管腔から排出し、そして該透析液
を該第一の管腔から該排液容器へとポンピングする、請求項11に記載のシステ
ム。 - 【請求項15】 前記カテーテルが二重管腔カテーテルである、請求項14
に記載のシステム。 - 【請求項16】 前記第一および第二のセンサが二重インライン圧力/減圧
センサである、請求項11に記載のシステム。 - 【請求項17】 患者を透析する方法であって、以下の工程: カテーテルを該患者の腹膜に配置する工程; 少なくとも1つの透析液容器を提供する工程; 該透析液容器を第一の管腔で該カテーテルに接続する工程であって、該第一の
管腔が、該カテーテルと該透析液容器との間でインラインで配置される第一の圧
力センサを備える、工程; 少なくとも1つの排液容器を提供する工程; 該排液容器を第二の管腔で該カテーテルに接続する工程であって、該第二の管
腔が、該カテーテルと該排液容器との間でインラインで配置される第二の圧力セ
ンサを備える、工程; 透析液を該透析液容器から該患者の腹膜へと移動させ、そして該患者の腹腔内
圧を該第二の圧力センサでモニタリングする工程;ならびに 透析液を該患者の該腹膜から該排液容器へと移動させ、そして該患者の腹腔内
圧を該第一の圧力センサでモニタリングする工程、 を包含する、方法。 - 【請求項18】 前記透析液を前記透析液容器から前記患者の前記腹膜へと
移動させる工程が、透析液を該透析液容器から該患者へと、該透析液容器と前記
第一圧力センサとの間にインラインで配置された第一ポンプを用いてポンピング
する工程をさらに包含する、請求項17に記載の方法。 - 【請求項19】 前記透析液を前記患者の腹膜から前記排液容器へと移動さ
せる工程が、透析液を該患者の腹膜から該排液容器へと、該排液容器と前記第二
の圧力センサとの間にインラインで配置される第二のポンプを用いてポンピング
する工程をさらに包含する、請求項17に記載の方法。 - 【請求項20】 前記透析液容器が、前記患者の前記腹膜の垂直方向上方に
配置され、そして透析液を該透析液容器から該患者の該腹膜へと移動させる工程
が、透析液を該透析液容器から該患者へと、静水圧頭のもとで流す工程をさらに
包含する、請求項17に記載の方法。 - 【請求項21】 前記排液容器が、前記患者の前記腹膜の垂直方向下方に配
置され、そして透析液を該患者の該腹膜から該排液容器へと移動させる工程が、
透析液を該患者の該腹膜から該排液容器へと静水圧頭のもとで流す工程をさらに
包含する、請求項17に記載の方法。
Applications Claiming Priority (3)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US09/501,778 US6497676B1 (en) | 2000-02-10 | 2000-02-10 | Method and apparatus for monitoring and controlling peritoneal dialysis therapy |
US09/501,778 | 2000-02-10 | ||
PCT/US2001/004083 WO2001058509A1 (en) | 2000-02-10 | 2001-02-08 | Method and apparatus for monitoring and controlling peritoneal dialysis therapy |
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ES (1) | ES2266160T3 (ja) |
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- 2001-02-08 AT AT01907123T patent/ATE330647T1/de active
- 2001-02-08 WO PCT/US2001/004083 patent/WO2001058509A1/en active IP Right Grant
- 2001-02-08 MX MXPA02007765A patent/MXPA02007765A/es active IP Right Grant
- 2001-02-08 ES ES01907123T patent/ES2266160T3/es not_active Expired - Lifetime
- 2001-02-08 EP EP01907123A patent/EP1253954B1/en not_active Expired - Lifetime
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- 2001-02-08 AU AU2001234940A patent/AU2001234940A1/en not_active Abandoned
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2006
- 2006-12-28 US US11/617,543 patent/US8323231B2/en not_active Expired - Fee Related
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JP2014167291A (ja) * | 2006-04-14 | 2014-09-11 | Deka Products Lp | 流体圧送、熱交換、熱検知および伝導率検知用システム、器具および方法 |
JP2010523230A (ja) * | 2007-04-05 | 2010-07-15 | ベロメディックス,インク | 自動治療システム及び方法 |
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JP2018505015A (ja) * | 2014-12-17 | 2018-02-22 | ニューソル・テクノロジーズ・インコーポレイテッド | 腹膜透析のためのシステムおよび方法 |
JP2020520268A (ja) * | 2017-05-16 | 2020-07-09 | フレゼニウス メディカル ケア ドイッチェランド ゲゼルシャフト ミット ベシュレンクテル ハフツング | 腹膜透析を実行するための装置 |
JP7309618B2 (ja) | 2017-05-16 | 2023-07-18 | フレゼニウス メディカル ケア ドイッチェランド ゲゼルシャフト ミット ベシュレンクテル ハフツング | 腹膜透析を実行するための装置 |
Also Published As
Publication number | Publication date |
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US8323231B2 (en) | 2012-12-04 |
CO5280187A1 (es) | 2003-05-30 |
US7507220B2 (en) | 2009-03-24 |
US20130150780A1 (en) | 2013-06-13 |
DE60120922D1 (de) | 2006-08-03 |
TW503097B (en) | 2002-09-21 |
US20170014566A1 (en) | 2017-01-19 |
US6497676B1 (en) | 2002-12-24 |
JP4557484B2 (ja) | 2010-10-06 |
US20020120227A1 (en) | 2002-08-29 |
AR032148A1 (es) | 2003-10-29 |
WO2001058509A1 (en) | 2001-08-16 |
ES2266160T3 (es) | 2007-03-01 |
US20070135758A1 (en) | 2007-06-14 |
EP1253954B1 (en) | 2006-06-21 |
DK1253954T3 (da) | 2006-10-23 |
AU2001234940A1 (en) | 2001-08-20 |
US9474842B2 (en) | 2016-10-25 |
MXPA02007765A (es) | 2002-10-11 |
DE60120922T2 (de) | 2007-02-01 |
US8172789B2 (en) | 2012-05-08 |
US8206339B2 (en) | 2012-06-26 |
ATE330647T1 (de) | 2006-07-15 |
US10322224B2 (en) | 2019-06-18 |
US6592542B2 (en) | 2003-07-15 |
EP1253954A1 (en) | 2002-11-06 |
US20030204162A1 (en) | 2003-10-30 |
US20110028892A1 (en) | 2011-02-03 |
US20090198174A1 (en) | 2009-08-06 |
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