JPH058025B2 - - Google Patents
Info
- Publication number
- JPH058025B2 JPH058025B2 JP60186969A JP18696985A JPH058025B2 JP H058025 B2 JPH058025 B2 JP H058025B2 JP 60186969 A JP60186969 A JP 60186969A JP 18696985 A JP18696985 A JP 18696985A JP H058025 B2 JPH058025 B2 JP H058025B2
- Authority
- JP
- Japan
- Prior art keywords
- blood
- hollow fiber
- fiber membrane
- membrane
- processing device
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Expired - Fee Related
Links
- 239000008280 blood Substances 0.000 claims description 128
- 210000004369 blood Anatomy 0.000 claims description 128
- 239000012528 membrane Substances 0.000 claims description 68
- 239000012510 hollow fiber Substances 0.000 claims description 55
- 229910052760 oxygen Inorganic materials 0.000 claims description 23
- 239000001301 oxygen Substances 0.000 claims description 23
- 239000007789 gas Substances 0.000 claims description 22
- QVGXLLKOCUKJST-UHFFFAOYSA-N atomic oxygen Chemical compound [O] QVGXLLKOCUKJST-UHFFFAOYSA-N 0.000 claims description 21
- XLYOFNOQVPJJNP-UHFFFAOYSA-N water Substances O XLYOFNOQVPJJNP-UHFFFAOYSA-N 0.000 claims description 20
- 102000004169 proteins and genes Human genes 0.000 claims description 6
- 108090000623 proteins and genes Proteins 0.000 claims description 6
- 229920002492 poly(sulfone) Polymers 0.000 claims description 5
- 239000012466 permeate Substances 0.000 claims description 3
- 229920001296 polysiloxane Polymers 0.000 claims description 3
- 102000009027 Albumins Human genes 0.000 claims description 2
- 108010088751 Albumins Proteins 0.000 claims description 2
- 229920000098 polyolefin Polymers 0.000 claims description 2
- CURLTUGMZLYLDI-UHFFFAOYSA-N Carbon dioxide Chemical compound O=C=O CURLTUGMZLYLDI-UHFFFAOYSA-N 0.000 description 24
- 229910002092 carbon dioxide Inorganic materials 0.000 description 12
- 239000001569 carbon dioxide Substances 0.000 description 12
- 210000004072 lung Anatomy 0.000 description 11
- 239000007788 liquid Substances 0.000 description 9
- 239000012530 fluid Substances 0.000 description 7
- 238000010586 diagram Methods 0.000 description 5
- 230000000740 bleeding effect Effects 0.000 description 4
- 239000000835 fiber Substances 0.000 description 4
- 230000035699 permeability Effects 0.000 description 4
- 210000001367 artery Anatomy 0.000 description 3
- 230000000694 effects Effects 0.000 description 3
- 239000000706 filtrate Substances 0.000 description 3
- 230000037452 priming Effects 0.000 description 3
- 229920002301 cellulose acetate Polymers 0.000 description 2
- 150000002926 oxygen Chemical class 0.000 description 2
- 230000002093 peripheral effect Effects 0.000 description 2
- 229920002635 polyurethane Polymers 0.000 description 2
- 239000004814 polyurethane Substances 0.000 description 2
- 229920005989 resin Polymers 0.000 description 2
- 239000011347 resin Substances 0.000 description 2
- 238000001356 surgical procedure Methods 0.000 description 2
- 210000003462 vein Anatomy 0.000 description 2
- 206010013496 Disturbance in attention Diseases 0.000 description 1
- 206010018873 Haemoconcentration Diseases 0.000 description 1
- 238000010790 dilution Methods 0.000 description 1
- 239000012895 dilution Substances 0.000 description 1
- 238000005516 engineering process Methods 0.000 description 1
- 239000000463 material Substances 0.000 description 1
- 229920003002 synthetic resin Polymers 0.000 description 1
- 239000000057 synthetic resin Substances 0.000 description 1
Landscapes
- Investigating Or Analysing Biological Materials (AREA)
- External Artificial Organs (AREA)
Description
【発明の詳細な説明】
〔産業上の利用分野〕
この発明は、手術時に患者の生体外に連結して
血液に酸素を供給し二酸化炭素を除去しながら増
加した上記血液中の水分を除去して正常な水分量
の血液にするための血液処理装置に関するもので
ある。[Detailed Description of the Invention] [Field of Industrial Application] This invention is connected to a patient's body outside the body during surgery to supply oxygen to the blood, remove carbon dioxide, and remove increased water in the blood. The present invention relates to a blood processing device for converting blood to a normal water content.
従来のこの種装置としては第３図に示すものが
ある。この血液処理装置はその主体となる人工肺
４と血液濃縮器９とが分離されていた。すなわち
一方側が血液ポンプ２、心内血貯血槽３、血液フ
イルター１５を配置した第１の液回路５を介して
生体の手術部出血部位１に連結され、またこの側
の液回路１１Ａを介して静脈Ｄに連結されてお
り、他方側がガスフイルター１６を配置した気体
回路１１Ｂを介して外部に連結され、またこの側
の血液ポンプ１７、血液フイルター１５を配置し
た第２の液回路１２を介して動脈Ｅに連結される
ことで、患者の血液に酸素を供給し、二酸化炭素
を除去する人工肺４と、一方側の血液入口ポート
９ａは血液ポンプ１８を配置した液回路１３を介
して人工肺４側に連結され、他方側の血液出口ポ
ート９ｂは液回路１９を介して前記の心内血貯血
槽３に連結されることで、患者の水分は透過する
がタンパク質は阻止する多数の中空繊維膜を集束
状に内臓した血液濃縮器９とが、上記による血液
処理装置の液回路に分離して並列ループ状に配置
されていた。この場合上記血液濃縮器９の主体と
なる中空繊維膜は、セルロースアセテートにより
構成されていた。このセルロースアセテートは透
水速度が0.2〜0.3／m2・分・Kg／cm2と低く、除
水効率が悪いので、除水効率を高めるために繊維
の内径を小さくし、かつ繊維長を長くする必要が
あり、その結果人工肺の血液量と同じ流量で血液
を流そうとすると圧力損失が過大なものになつて
しまい、生体外に設置する人工肺４と直列状に連
結できなかつた。従つてこの血液濃縮器９は前記
により生体外に連結された人工肺４と分離して並
列ループ状に配置されていた。なお第３図に示す
血液濃縮器９の排水ポート９ｃは、圧力計２１付
の吸引ボトル２０を配置した液回路１４を介して
陰圧源Ｇに連結されている。
A conventional device of this type is shown in FIG. In this blood processing apparatus, an artificial lung 4 and a hemoconcentrator 9, which are the main components thereof, are separated. That is, one side is connected to the surgical site bleeding site 1 of the living body via a first liquid circuit 5 in which a blood pump 2, an intracardiac blood reservoir 3, and a blood filter 15 are arranged, and also via a liquid circuit 11A on this side. It is connected to the vein D, and is connected to the outside via a gas circuit 11B in which a gas filter 16 is arranged on the other side, and via a second liquid circuit 12 in which a blood pump 17 and a blood filter 15 are arranged on this side. The oxygenator 4 is connected to the artery E to supply oxygen to the patient's blood and remove carbon dioxide, and the blood inlet port 9a on one side is connected to the oxygenator via a fluid circuit 13 in which a blood pump 18 is arranged. 4 side, and the blood outlet port 9b on the other side is connected to the intracardiac blood reservoir 3 via the fluid circuit 19, so that a large number of hollow fibers are connected to the intracardiac blood reservoir 3 through the fluid circuit 19, so that a large number of hollow fibers are connected to each other to allow patient's water to pass through but to block proteins. A hemoconcentrator 9 containing membranes in a bundled manner was separated from the liquid circuit of the blood processing apparatus described above and arranged in a parallel loop. In this case, the hollow fiber membrane serving as the main body of the hemoconcentrator 9 was composed of cellulose acetate. This cellulose acetate has a low water permeation rate of 0.2 to 0.3/ m2 /m2/min/Kg/ cm2 , resulting in poor water removal efficiency.In order to improve water removal efficiency, the inner diameter of the fibers is made smaller and the fiber length is increased. As a result, when trying to flow blood at the same flow rate as the blood volume of the oxygenator, the pressure loss would become excessive, making it impossible to connect in series with the oxygenator 4 installed outside the living body. Therefore, this hemoconcentrator 9 was arranged in a parallel loop, separated from the artificial lung 4 connected outside the living body. The drain port 9c of the hemoconcentrator 9 shown in FIG. 3 is connected to a negative pressure source G via a liquid circuit 14 in which a suction bottle 20 with a pressure gauge 21 is disposed.
上記の構成により、従来の血液処理装置には次
のような問題点があつた。
Due to the above configuration, the conventional blood processing apparatus has the following problems.
(1) 血液濃縮器に内蔵されている中空繊維膜の透
水速度が低いので濃縮効率が悪かつた。(1) The hollow fiber membrane built into the hemoconcentrator had a low water permeation rate, resulting in poor concentration efficiency.
(2) 生体外に設置する人工肺の回路とは別に血液
濃縮器の専用回路が並列ループ状に必要である
ため、回路の構成が複雑になり、またそれぞれ
の回路に血液ポンプが必要になり、これによつ
て血液処理操作が繁雑になつた。(2) A dedicated circuit for the hemoconcentrator is required in a parallel loop in addition to the circuit for the oxygenator installed outside the body, making the circuit configuration complex and requiring a blood pump for each circuit. This made blood processing operations complicated.
(3) 並列ループ回路の構成であるため、プライミ
ング量（血液充填量）が多くなり、患者の血液
希釈量が多くなつてしまう。(3) Because of the parallel loop circuit configuration, the priming amount (blood filling amount) increases, resulting in an increased amount of blood dilution in the patient.
この発明は、上記従来技術の問題点を解決する
ものであり、血液濃縮器の中空繊維膜の濃縮効率
を良くして人工肺に続くハウジング内へ収納を可
能にし、これによつて回路構成が簡単になり、ポ
ンプも１台で済んで血液処理操作が容易にでき、
かつプライミング量（血液充填量）を少なくでき
る血液処理装置を提供することにある。 The present invention solves the above-mentioned problems of the prior art, improves the concentration efficiency of the hollow fiber membrane of a hemoconcentrator, enables it to be housed in a housing next to an oxygenator, and thereby improves the circuit configuration. It is simple and requires only one pump, making blood processing operations easier.
Another object of the present invention is to provide a blood processing device that can reduce the amount of priming (the amount of blood filled).
本発明者らは、ポリスルホンからなる半透膜が
透水性に優れ血液濃縮膜として優れた特性を有す
ることを見出し、先に特許出願を行つた。そして
さらに検討を行つた結果、かかる透水性に優れた
中空繊維膜を内蔵する血液濃縮装置と人工肺装置
とを直列に連結することにより上記問題点を解決
し得ることを見出し、本発明に到達した。すなわ
ち本発明は、ガス交換能をもつて血液に酸素を供
給し二酸化炭素を除去する第１の中空繊維膜によ
りなる人工肺と、水分は迅速に透過するがタンパ
ク質は確実に阻止する第２の中空繊維膜によりな
る血液濃縮器とが同一のハウジング内に直列の連
結体をもつて収納配置されてなり、このハウジン
グには第１または第２の中空繊維膜内面と連通す
る血液の入口、出口および第１の中空繊維膜外面
と連通する酸素、酸素含有ガスの入口、出口並び
に第２の中空繊維膜外面と連通する排水口がそれ
ぞれ設けられたことにある。
The present inventors have discovered that a semipermeable membrane made of polysulfone has excellent water permeability and excellent properties as a blood concentrating membrane, and have previously filed a patent application. As a result of further studies, it was discovered that the above-mentioned problems could be solved by connecting in series a hemoconcentrator that incorporates a hollow fiber membrane with excellent water permeability and an artificial lung device, leading to the present invention. did. That is, the present invention consists of an artificial lung made of a first hollow fiber membrane that has gas exchange ability to supply oxygen to blood and remove carbon dioxide, and a second artificial lung that allows moisture to permeate quickly but reliably blocks protein. A blood concentrator made of a hollow fiber membrane is housed in the same housing with a serial connection, and the housing has a blood inlet and an outlet communicating with the inner surface of the first or second hollow fiber membrane. and an inlet and an outlet for oxygen and oxygen-containing gas communicating with the outer surface of the first hollow fiber membrane, and a drainage port communicating with the outer surface of the second hollow fiber membrane.
この発明による血液処理装置を使用する際は、
患者の静脈血を液回路を介して血液処理装置の血
液入口ポート側に導入させ、また手術部出血部位
よりの血液は従来例と同様に、第１の液回路に配
置されてる血液ポンプ、心内血貯血槽、血液フイ
ルターを経てこれも同じ血液入口に流入させるよ
うに連結し、さらに上記装置の血液出口は従来図
で示す血液ポンプと血液フイルターを配置した第
２の液回路を介して処理済の血液を動脈側に戻す
ように連結するとともに、上記装置のガス入口を
酸素供給源に連結し、排水口は従来図で示した吸
引ボトル付の液回路を介して陰圧源に連結するこ
とにより、上記の装置に内蔵されている第１の中
空繊維膜は、人工肺としての機能を発揮して血液
に酸素を供給し二酸化炭素を除去するうえ、第２
の中空繊維膜は、血液濃縮器の機能を発揮して上
記血液中の水分を除去する。
When using the blood processing device according to the present invention,
The patient's venous blood is introduced into the blood inlet port side of the blood processing device via the fluid circuit, and the blood from the bleeding site at the surgical site is introduced into the blood pump, which is placed in the first fluid circuit, and the heart. The internal blood reservoir is connected to the blood filter so that it also flows into the same blood inlet, and the blood outlet of the above device is processed through a second fluid circuit in which a blood pump and a blood filter are arranged as shown in the conventional diagram. At the same time, the gas inlet of the device is connected to an oxygen supply source, and the drain port is connected to a negative pressure source via a liquid circuit with a suction bottle as shown in the conventional diagram. As a result, the first hollow fiber membrane built into the above device functions as an artificial lung to supply oxygen to the blood and remove carbon dioxide, and the second hollow fiber membrane functions as an artificial lung to supply oxygen to the blood and remove carbon dioxide.
The hollow fiber membrane functions as a hemoconcentrator to remove water from the blood.
以下、この発明の実施例を添付図面に基づいて
説明する。
Embodiments of the present invention will be described below with reference to the accompanying drawings.
第１図はこの発明による血液処理装置Ａの一実
施例を示すものである。上記の血液処理装置Ａは
次のように構成されている。すなわちこの血液処
理装置Ａは、合成樹脂材等をもつてその外郭が長
手方向の前後端を閉塞した筒状体によりハウジン
グ６に形成されている。このハウジング６は、長
手方向の初端側中心位置に未処理血液F1の導入
口となる血液入口ポート６ａが、また終端側中心
位置には処理済血液F2の排出口となる血液出口
ポート６ｂがそれぞれ軸方向に突設されている。
そしてこのハウジング６の外周面の一端側で、人
工肺Ｂが収納されている初端側の上記血液入口ポ
ート６ａに近傍する外周位置には二酸化炭素CO2
の排気口となるガス出口ポート６ｃ害、またこの
同じ側の中途部位置には酸素O2の給気口となる
ガス入口ポート６ｄがそれぞれ径方向に突設され
ている。さらに上記ハウジング６の同じ外周面の
一端側で、血液濃縮器Ｃが収納されている終端側
にあたり、かつ上記ガス入口ポート６ｄに近傍す
る外周位置には濾過液Ｈの除水口となる排水ポー
ト６ｅが径方向に突設されている。 FIG. 1 shows an embodiment of a blood processing apparatus A according to the present invention. The blood processing apparatus A described above is configured as follows. That is, this blood processing apparatus A has a housing 6 formed of a cylindrical body made of synthetic resin or the like and whose outer shell is closed at its front and rear ends in the longitudinal direction. This housing 6 has a blood inlet port 6a, which serves as an inlet for untreated blood F1 , at the center position on the first end side in the longitudinal direction, and a blood outlet port, which serves as an outlet for the treated blood F2 , at the center position on the terminal end side. 6b are provided to protrude in the axial direction.
On one end side of the outer peripheral surface of this housing 6, carbon dioxide CO 2 is placed on the outer peripheral position near the blood inlet port 6a on the initial end side where the oxygenator B is housed.
A gas outlet port 6c, which serves as an exhaust port for O 2 , and a gas inlet port 6d, which serves as an air supply port for oxygen O 2 , are protruded in the radial direction at a midway position on the same side. Further, on one end side of the same outer circumferential surface of the housing 6, a drain port 6e serving as a water removal port for the filtrate H is located at the outer circumferential position near the terminal side where the hemoconcentrator C is housed and near the gas inlet port 6d. protrudes in the radial direction.
上記によるハウジング６の初端側にあたる長手
方向の半身部強内すなわち前記によりガス出口ポ
ート６ｃとガス入口ポート６ｄとを突設した側に
あたる他方を若干上回る円筒部内には、シリコー
ン膜よりなる多数の第１中空繊維膜７が、円柱状
に集束された状態をもつてその両端に対するポリ
ウレタン等の硬化性樹脂１０により気密に固着さ
れており、その両端面を径方向に切断されること
で中空糸膜内を軸方向へ流通する血液に径方向か
ら酸素O2を供給し、この酸素O2とを交換されて
上記血液中の二酸化炭素CO2が径方向へ排出され
るよう構成されている。これによつて人工肺の機
能を発揮するように構成された膜型の人工肺Ｂが
長手方向の半身部に収納配置されることになる。 Inside the longitudinal half of the housing 6 on the initial end side, that is, in the cylindrical portion slightly above the other side on which the gas outlet port 6c and the gas inlet port 6d are protruded, there are a number of silicone membranes. The first hollow fiber membrane 7 is bundled into a cylindrical shape and is airtightly fixed to both ends thereof with a curable resin 10 such as polyurethane. The membrane is configured such that oxygen O 2 is supplied from the radial direction to the blood flowing in the axial direction within the membrane, and the oxygen O 2 is exchanged with the carbon dioxide CO 2 in the blood to be discharged radially. As a result, the membrane-type oxygenator B configured to perform the function of an oxygenator is housed in the longitudinal half of the body.
また上記ハウジング６の終端側にあたる長手方
向の半身部弱内すなわち前記により排水ポート６
ｅを突設した側にあたる他方を若干下回る円筒部
内には透水速度が大きくタンパク質阻止率の高い
ポリスルホン膜よりなる多数の第２中空繊維膜８
が、円柱状に集束された状態をもつてその両端を
上記と同様にポリウレタン等の硬化性樹脂１０に
より気密に固着されており、その両端面を径方向
に切断されることで中空糸膜内を軸方向へ流通す
る血液中から水分は径方向へ透過されるがタンパ
ク質は阻止されるよう構成されている。これによ
つて血液濃縮の機能を発揮するように構成された
血液濃縮器Ｃが長手方向の半身部に収納配置され
ることになる。 In addition, the drain port 6 is located in the longitudinal half of the housing 6 on the terminal side, i.e., as described above.
Inside the cylindrical portion slightly below the other side on the protruding side of e are a number of second hollow fiber membranes 8 made of polysulfone membranes that have a high water permeability rate and a high protein rejection rate.
are bundled into a cylindrical shape, and both ends are hermetically fixed with a curable resin 10 such as polyurethane in the same manner as above, and by cutting both end faces in the radial direction, the inside of the hollow fiber membrane is The structure is such that water from blood flowing in the axial direction permeates in the radial direction, but proteins are blocked. As a result, the hemoconcentrator C configured to perform the function of hemoconcentration is housed in the longitudinal half of the body.
上記により第１中空繊維膜７と第２中空繊維膜
８とがハウジング６内に直列に収納配置されたの
で、血液入口ポート６ａと第１中空繊維膜７の内
面とが連通し、また血液出口ポート６ｂと第２中
空繊維膜８とが連通するうえ、上記両中空繊維膜
７，８の双方内面も隣接端部において連通し、こ
れによつて一方の血液入口ポート６ａから給入さ
れた未処理血液F1に人工肺Ｂの位置で酸素O2を
供給し、この酸素O2と交換されて二酸化炭素CO2
を除去させたのち、次の血液濃縮器Ｃの位置では
余分な水分の濾過液Ｈを除水させて、他方の血液
出口ポート６ｂから正常な処理済血液F2として
排出することができる一括体の血液処理装置Ａを
構成することができる。なお、前記各中空繊維膜
の端部には貯血間隙６ｆが設けられる。 Since the first hollow fiber membrane 7 and the second hollow fiber membrane 8 are housed and arranged in series in the housing 6 as described above, the blood inlet port 6a and the inner surface of the first hollow fiber membrane 7 are in communication with each other, and the blood outlet port 6a is in communication with the inner surface of the first hollow fiber membrane 7. The port 6b and the second hollow fiber membrane 8 communicate with each other, and the inner surfaces of both hollow fiber membranes 7 and 8 also communicate with each other at their adjacent ends, thereby allowing blood inlet from one of the blood inlet ports 6a to be in communication with the second hollow fiber membrane 8. Oxygen O 2 is supplied to the treated blood F 1 at the location of the oxygenator B, and this oxygen O 2 is exchanged with carbon dioxide CO 2
After removing the excess water, the filtrate H is removed at the next hemoconcentrator C position, and the bulk body is discharged as normal processed blood F2 from the other blood outlet port 6b. The blood processing apparatus A can be configured as follows. Incidentally, a blood storage gap 6f is provided at the end of each hollow fiber membrane.
上記の構成による血液処理装置Ａを用いて手術
を行う場合は、第２図に示すように患者の静脈Ｄ
における未処理血液F1がこの側の液回路１１Ａ
を介して血液処理装置Ａの血液入口ポート６ａに
導入されるように連結し、また上記患者の手術部
出血部位１は、この手術部において出血中の未処
理血液F1が第１の液回路５に配置された血液ポ
ンプ２、心内血貯血槽３、血液フイルター１５の
部材を経て上記と同じ血液入口ポート６ａに流入
するように連結する。そしてさらに血液処理装置
Ａの血液出口ポート６ｂは、血液ポンプ１７と血
液フイルター１５を配置した第２の液回路１２を
介して処理済の血液F2を動脈Ｅへ戻すように連
結し、かつ血液処理装置Ａのガス入口ポート６ｄ
には酸素O2の供給管を、またガス出口ポート６
ｃには二酸化炭素CO2の排出管を、更にまた排水
ポート６ｅには圧力計２１付の吸引ボルト２０を
配置した液回路１４をそれぞれ連結する。これに
よつて、上記血液処理装置Ａの血液入口ポート６
ａ内へ導入された未処理血液F1は、ハウジング
６内の初端側に収納配置されている第１中空繊維
膜７内へ流入してこの第１中空繊維膜７による人
工肺Ｂをもつて、上記未処理血液F1に酸素O2を
供給し、この酸素O2と交換されて上記血液中の
二酸化炭素CO2を除去することができる。そして
次に上記の血液が流出方向に配置されている第２
中空繊維膜８内へ流入してこの第２中空繊維膜８
による血液濃縮器Ｃをもつて、血液中の余剰水分
を径方向に除水することができる。このようにし
て人工肺Ｂと血液濃縮器Ｃとにより血液処理を施
されて正常化された処理済血液F2は、血液出口
ポート６ｂから前記の液回路を経て患者の動脈Ｅ
へ戻すことができる。なお血液濃縮器Ｃにおいて
除水された濾過液Ｈは、排水ポート６ｅからこの
位置に連結されている陰圧源側へ排出される。 When performing surgery using the blood processing apparatus A with the above configuration, the patient's vein D
The unprocessed blood F 1 is connected to the liquid circuit 11A on this side.
The blood inlet port 6a of the blood processing device A is connected to the blood inlet port 6a of the blood processing device A through the blood treatment device A, and the bleeding site 1 of the patient's surgical site is connected to the blood inlet port 6a of the blood processing device A. The blood is connected so as to flow into the same blood inlet port 6a as above through the blood pump 2, intracardiac blood reservoir 3, and blood filter 15 disposed at 5. Further, the blood outlet port 6b of the blood processing device A is connected to return the treated blood F2 to the artery E via the second fluid circuit 12 in which a blood pump 17 and a blood filter 15 are arranged, and the blood Gas inlet port 6d of processing device A
to the oxygen O 2 supply pipe, and also to the gas outlet port 6.
A discharge pipe for carbon dioxide CO 2 is connected to c, and a liquid circuit 14 in which a suction bolt 20 with a pressure gauge 21 is arranged is connected to the drain port 6e. Thereby, the blood inlet port 6 of the blood processing device A
The untreated blood F 1 introduced into A flows into the first hollow fiber membrane 7 housed on the front end side of the housing 6, and an oxygenator B is formed by this first hollow fiber membrane 7. Then, oxygen O 2 is supplied to the untreated blood F 1 and carbon dioxide CO 2 in the blood can be removed by being exchanged with the oxygen O 2 . And then the second blood is arranged in the outflow direction.
flows into the hollow fiber membrane 8 and this second hollow fiber membrane 8
With the hemoconcentrator C, excess water in the blood can be removed in the radial direction. The processed blood F2 , which has been processed and normalized by the artificial lung B and the hemoconcentrator C in this way, is passed from the blood outlet port 6b through the liquid circuit to the patient's artery E.
can be returned to. Note that the filtrate H from which water has been removed in the hemoconcentrator C is discharged from the drain port 6e to the negative pressure source connected to this position.
上記の実施例では、第１図に示すように、ハウ
ジング６の初端側すなわち血液入口ポート６ａ側
の内部に第１中空繊維膜７をもつてなるガス入口
ポート６ｄ、ガス出口ポート６ｃ付の人工肺Ｂを
配置し、また上記ハウジング６の終端側すなわち
血液出口ポート６ｂ側の内部には第２中空繊維膜
８をもつてなる排水ポート６ｅ付の血液濃縮器Ｃ
を配置することで血液処理装置Ａを構成したが、
この発明は上記の構成に限定することなく、例え
ばハウジング６の初端側（血液入口ポート６ａ
側）内部に第２中空繊維膜８をもつてなる排水ポ
ート６ｅ付の血液濃縮器Ｃを配置し、また上記ハ
ウジング６の終端側（血液出口ポート６ｂ側）内
部に第１中空繊維膜７をもつてなるガス入口ポー
ト６ｄ、ガス出口ポート６ｃ付の人工肺Ｂを配置
して血液処理装置Ａを構成しても、上記の実施例
と同様の作用効果が得られるものである。 In the above embodiment, as shown in FIG. 1, a gas inlet port 6d having a first hollow fiber membrane 7 and a gas outlet port 6c are provided inside the housing 6 on the initial end side, that is, on the blood inlet port 6a side. A hemoconcentrator C has an artificial lung B disposed therein, and has a second hollow fiber membrane 8 inside the terminal end side of the housing 6, that is, the blood outlet port 6b side, and has a drainage port 6e.
The blood processing device A was configured by arranging the
The present invention is not limited to the above-described configuration, but can be applied to, for example, the initial end side of the housing 6 (blood inlet port 6a).
side) A blood concentrator C with a drainage port 6e having a second hollow fiber membrane 8 is disposed inside the housing 6, and a first hollow fiber membrane 7 is disposed inside the terminal end side (blood outlet port 6b side) of the housing 6. Even if the blood processing apparatus A is configured by arranging an oxygenator B having a gas inlet port 6d and a gas outlet port 6c, the same effects as in the above embodiment can be obtained.
また上記の実施例では人工肺Ｂを構成する第１
中空繊維膜７をシリコーン膜により形成したが、
この発明は上記の素材に限定することなく、例え
ば多孔性ポリオレフイン膜やポリスルホン膜を用
いても、上記の実施例と同様に、未処理血液F1
に酸素O2を供給し、この酸素O2と交換されて上
記血液F1中の二酸化炭素CO2を除去することがで
きるものである。更に、第２中空繊維膜８は透水
速度が１／m2・分・Kg／cm2以上でアルブミン阻
止率が95％以上であることが好ましく、圧力損失
の点で内径が300〜800μ、長さが40〜140mmの範
囲にあることが好ましい。 Furthermore, in the above embodiment, the first
Although the hollow fiber membrane 7 was formed from a silicone membrane,
This invention is not limited to the above-mentioned materials; for example, even if a porous polyolefin membrane or a polysulfone membrane is used, the unprocessed blood F 1
It is capable of supplying oxygen O 2 to the blood F 1 and removing carbon dioxide CO 2 in the blood F 1 by being exchanged with this oxygen O 2 . Furthermore, it is preferable that the second hollow fiber membrane 8 has a water permeation rate of 1/m 2 ·min ·Kg/cm 2 or more and an albumin rejection rate of 95% or more. The length is preferably in the range of 40 to 140 mm.
この発明はガス交換能をもつて血液に酸素を供
給し二酸化炭素を除去する第１の中空繊維膜によ
りなる人工肺と、透水速度が大きくタンパク質を
確実に阻止する第２の中空繊維膜によりなる血液
濃縮器とがハウジング内に直列の連結体をつて収
納配置されてなり、このハウジングには第１また
は第２の中空繊維膜内面と連通する血液の入口ポ
ート、出口ポートおよび第１の中空繊維膜外面と
連通する酸素又は酸素含有ガスの入口ポート、出
口ポート並びに第２の中空繊維膜外面と連通する
排水ポートがそれぞれ設けられたことを特徴とす
るものである。従つてこの血液処理装置は、患者
の生体外に連結して使用した場合、透水速度の高
い第２中空繊維膜の使用により上記繊維の内径を
大きくかつ繊維長も短くできて血液濃縮器におけ
る圧力損失が減少し、これによつて人工肺と直列
に連結できるため、従来のような複雑な回路を要
しないで簡単な回路にすることができ、またポン
プも出血側を除き１台で済むことから、血液処理
操作が極めて容易になり、かつプライミング量
（血液充填量）も少なくすることができる等の効
果がある。
This invention consists of an artificial lung consisting of a first hollow fiber membrane that has gas exchange ability to supply oxygen to the blood and remove carbon dioxide, and a second hollow fiber membrane that has a high water permeation rate and reliably blocks proteins. A hemoconcentrator is disposed in a serial connection within the housing, the housing having a blood inlet port, an outlet port, and a first hollow fiber in communication with the inner surface of the first or second hollow fiber membrane. The membrane is characterized by being provided with an inlet port and an outlet port for oxygen or oxygen-containing gas communicating with the outer surface of the membrane, and a drainage port communicating with the outer surface of the second hollow fiber membrane. Therefore, when this blood processing device is connected to a patient's body outside the body, the inner diameter of the fibers can be increased and the fiber length can be shortened by using the second hollow fiber membrane with a high water permeability rate, thereby reducing the pressure in the hemoconcentrator. Loss is reduced, and as a result it can be connected in series with the oxygenator, a simple circuit can be created without the need for a complicated circuit like in the past, and only one pump is required except for the bleeding side. Therefore, the blood processing operation becomes extremely easy, and the priming amount (blood filling amount) can also be reduced.
第１図はこの発明の一実施例による血液処理装
置を示す縦断面図、第２図は第１図の実施例を使
用した血液処理回路構成図、第３図は従来例の血
液処理装置を説明するための血液処理回路図であ
る。
６……ハウジング、６ａ……血液入口ポート、
６ｂ……血液出口ポート、６ｃ……ガス出口ポー
ト、６ｄ……ガス入口ポート、６ｅ……排水ポー
ト、７……第１中空繊維膜、８……第２中空繊維
膜、Ａ……血液処理装置、Ｂ……人工肺、Ｃ……
血液濃縮器。
FIG. 1 is a longitudinal sectional view showing a blood processing device according to an embodiment of the present invention, FIG. 2 is a configuration diagram of a blood processing circuit using the embodiment of FIG. 1, and FIG. 3 is a diagram showing a conventional blood processing device. It is a blood processing circuit diagram for explanation. 6...Housing, 6a...Blood inlet port,
6b...Blood outlet port, 6c...Gas outlet port, 6d...Gas inlet port, 6e...Drainage port, 7...First hollow fiber membrane, 8...Second hollow fiber membrane, A...Blood processing Apparatus, B... Artificial lung, C...
Hemoconcentrator.
Claims (1)
は透過するがタンパク質は阻止する第２の中空繊
維膜とがハウジング内に直列の連結状態に収納さ
れてなり、該ハウジングには前記第１または第２
の中空繊維膜内面と連通する血液の入口、出口お
よび第１の中空繊維膜外面と連通する酸素又は酸
素含有ガスの入口、出口並びに第２の中空繊維膜
外面と連通する排水口がそれぞれ設けられている
ことを特徴とする血液処理装置。 ２ 前記血液入口が第１の中空繊維膜内面と連通
し、前記血液出口が第２の中空繊維膜内面と連通
する特許請求の範囲第１項記載の血液処理装置。 ３ 前記血液入口が第２の中空繊維膜内面と連通
し、前記血液出口が第１の中空繊維膜内面と連通
する特許請求の範囲第１項記載の血液処理装置。 ４ 前記第２の中空繊維膜の透水速度が１／
m2・分・Kg／cm2以上でアルブミン阻止率が95％以
上である特許請求の範囲第１項ないし第３項のい
ずれかの項に記載の血液処理装置。 ５ 前記第１の中空繊維膜がシリコーン膜、多孔
性ポリオレフイン膜またはポリスルホン膜よりな
る特許請求の範囲第１項ないし第４項のいずれか
の項に記載の血液処理装置。 ６ 前記第２の中空繊維膜がポリスルホン膜より
なる特許請求の範囲第１項ないし第５項のいずれ
かの項に記載の血液処理装置。[Scope of Claims] 1. A first hollow fiber membrane having gas exchange ability and a second hollow fiber membrane that permeates moisture but blocks protein, are housed in a housing in a serially connected state; The housing has the first or second
A blood inlet and outlet communicating with the inner surface of the hollow fiber membrane, an oxygen or oxygen-containing gas inlet and outlet communicating with the outer surface of the first hollow fiber membrane, and a drainage port communicating with the outer surface of the second hollow fiber membrane are provided, respectively. A blood processing device characterized by: 2. The blood processing device according to claim 1, wherein the blood inlet communicates with the inner surface of the first hollow fiber membrane, and the blood outlet communicates with the inner surface of the second hollow fiber membrane. 3. The blood processing device according to claim 1, wherein the blood inlet communicates with the inner surface of the second hollow fiber membrane, and the blood outlet communicates with the inner surface of the first hollow fiber membrane. 4 The water permeation rate of the second hollow fiber membrane is 1/
The blood processing device according to any one of claims 1 to 3, wherein the albumin rejection rate is 95% or more at m 2 ·min·Kg/cm 2 or more. 5. The blood treatment device according to any one of claims 1 to 4, wherein the first hollow fiber membrane is a silicone membrane, a porous polyolefin membrane, or a polysulfone membrane. 6. The blood processing device according to any one of claims 1 to 5, wherein the second hollow fiber membrane is made of a polysulfone membrane.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP60186969A JPS6247369A (en) | 1985-08-26 | 1985-08-26 | Blood treatment apparatus |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP60186969A JPS6247369A (en) | 1985-08-26 | 1985-08-26 | Blood treatment apparatus |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| JPS6247369A JPS6247369A (en) | 1987-03-02 |
| JPH058025B2 true JPH058025B2 (en) | 1993-02-01 |
Family
ID=16197892
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP60186969A Granted JPS6247369A (en) | 1985-08-26 | 1985-08-26 | Blood treatment apparatus |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JPS6247369A (en) |
Families Citing this family (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| DE102009008601A1 (en) * | 2009-02-12 | 2010-08-19 | Novalung Gmbh | Device for the treatment of a biological fluid |
| JP5347602B2 (en) * | 2009-03-16 | 2013-11-20 | 株式会社ジェイ・エム・エス | Blood processing equipment |
-
1985
- 1985-08-26 JP JP60186969A patent/JPS6247369A/en active Granted
Also Published As
| Publication number | Publication date |
|---|---|
| JPS6247369A (en) | 1987-03-02 |
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