JPH0520334Y2 - - Google Patents
Info
- Publication number
- JPH0520334Y2 JPH0520334Y2 JP1988003644U JP364488U JPH0520334Y2 JP H0520334 Y2 JPH0520334 Y2 JP H0520334Y2 JP 1988003644 U JP1988003644 U JP 1988003644U JP 364488 U JP364488 U JP 364488U JP H0520334 Y2 JPH0520334 Y2 JP H0520334Y2
- Authority
- JP
- Japan
- Prior art keywords
- blood
- pressure
- flow rate
- blood pump
- setting circuit
- 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 - Lifetime
Links
- 239000008280 blood Substances 0.000 claims description 74
- 210000004369 blood Anatomy 0.000 claims description 74
- 210000004072 lung Anatomy 0.000 claims description 13
- 230000004087 circulation Effects 0.000 claims description 10
- 230000017531 blood circulation Effects 0.000 claims description 8
- 230000004044 response Effects 0.000 claims description 2
- 210000004204 blood vessel Anatomy 0.000 description 4
- 230000036772 blood pressure Effects 0.000 description 3
- 238000010241 blood sampling Methods 0.000 description 3
- 239000012510 hollow fiber Substances 0.000 description 3
- 238000011144 upstream manufacturing Methods 0.000 description 3
- CURLTUGMZLYLDI-UHFFFAOYSA-N Carbon dioxide Chemical compound O=C=O CURLTUGMZLYLDI-UHFFFAOYSA-N 0.000 description 2
- 230000002159 abnormal effect Effects 0.000 description 2
- 239000007789 gas Substances 0.000 description 2
- 239000000463 material Substances 0.000 description 2
- 239000002504 physiological saline solution Substances 0.000 description 2
- 229920001296 polysiloxane Polymers 0.000 description 2
- 230000037452 priming Effects 0.000 description 2
- 230000000241 respiratory effect Effects 0.000 description 2
- 239000004925 Acrylic resin Substances 0.000 description 1
- 229920000178 Acrylic resin Polymers 0.000 description 1
- MYMOFIZGZYHOMD-UHFFFAOYSA-N Dioxygen Chemical compound O=O MYMOFIZGZYHOMD-UHFFFAOYSA-N 0.000 description 1
- UQONAEXHTGDOIH-AWEZNQCLSA-N O=C(N1CC[C@@H](C1)N1CCCC1=O)C1=CC2=C(NC3(CC3)CCO2)N=C1 Chemical compound O=C(N1CC[C@@H](C1)N1CCCC1=O)C1=CC2=C(NC3(CC3)CCO2)N=C1 UQONAEXHTGDOIH-AWEZNQCLSA-N 0.000 description 1
- 239000004743 Polypropylene Substances 0.000 description 1
- BZHJMEDXRYGGRV-UHFFFAOYSA-N Vinyl chloride Chemical compound ClC=C BZHJMEDXRYGGRV-UHFFFAOYSA-N 0.000 description 1
- 238000013459 approach Methods 0.000 description 1
- QVGXLLKOCUKJST-UHFFFAOYSA-N atomic oxygen Chemical compound [O] QVGXLLKOCUKJST-UHFFFAOYSA-N 0.000 description 1
- 229910002092 carbon dioxide Inorganic materials 0.000 description 1
- 239000001569 carbon dioxide Substances 0.000 description 1
- 230000002950 deficient Effects 0.000 description 1
- 238000001514 detection method Methods 0.000 description 1
- 238000010586 diagram Methods 0.000 description 1
- 229910001882 dioxygen Inorganic materials 0.000 description 1
- 230000000694 effects Effects 0.000 description 1
- 230000000004 hemodynamic effect Effects 0.000 description 1
- 238000001990 intravenous administration Methods 0.000 description 1
- 239000007788 liquid Substances 0.000 description 1
- 239000012528 membrane Substances 0.000 description 1
- 238000000034 method Methods 0.000 description 1
- 229910052760 oxygen Inorganic materials 0.000 description 1
- 239000001301 oxygen Substances 0.000 description 1
- 229920002492 poly(sulfone) Polymers 0.000 description 1
- -1 polypropylene Polymers 0.000 description 1
- 229920001155 polypropylene Polymers 0.000 description 1
- 229920002635 polyurethane Polymers 0.000 description 1
- 239000004814 polyurethane Substances 0.000 description 1
- 238000000926 separation method Methods 0.000 description 1
Landscapes
- External Artificial Organs (AREA)
Description
【考案の詳細な説明】
（産業上の利用分野）
本考案は呼吸補助を長期間安全に実施すること
のできる人工補助肺装置に関するものである。[Detailed Description of the Invention] (Field of Industrial Application) The present invention relates to an artificial lung assist device that can safely provide respiratory assistance for a long period of time.
（従来の技術）
従来のこの種人工補助肺装置においては、体外
循環回路中に血液ポンプと人工肺を設けて、該血
液ポンプにて血液の体内循環量が一定となるよう
に体外循環を行わせていた。しかしながら上記体
外循環においては患者が不用意に動くことによつ
て採血部の先端が血管壁に接触したり、体外循環
回路が折れ曲つて回路が閉塞されると血液ポンプ
の吸引力によつて体外循環回路中に過度の陰圧を
生じて血管を傷つけたり、気泡を生じる危険があ
つた。そこで従来の装置では血液ポンプの上流側
に圧力計を設けて脱血不良状態により圧力計の圧
力が陰圧（例えば−25mmHg）となると警報を発
し、さらに脱血不良状態が進行し、圧力計の圧力
が過度の陰圧（例えば−50mmHg）となると血液
ポンプを停止させていた。また脱血不良状態が解
消されると血液ポンプが再び駆動するようにして
いる（例えば医器学 Vo157，Suppl.P44〜45
1987）。(Prior Art) In this type of conventional artificial lung assist device, a blood pump and an artificial lung are provided in the extracorporeal circulation circuit, and the blood pump performs extracorporeal circulation so that the amount of blood circulating in the body is constant. I was letting it go. However, in the above-mentioned extracorporeal circulation, if the tip of the blood sampling part comes into contact with the blood vessel wall due to careless movement of the patient, or if the extracorporeal circulation circuit is bent and the circuit is occluded, the suction force of the blood pump will cause the blood to be drawn out of the body. There was a risk of creating excessive negative pressure in the circulation circuit, damaging blood vessels or creating air bubbles. Therefore, in conventional devices, a pressure gauge is installed upstream of the blood pump, and if the pressure on the pressure gauge becomes negative pressure (for example -25 mmHg) due to poor blood removal, an alarm is issued. The blood pump was stopped when the pressure became excessively negative (eg -50 mmHg). In addition, when the poor blood removal condition is resolved, the blood pump is activated again (for example, Medical Science Vo157, Suppl. P44-45).
1987).
（考案が解決しようとする課題）
しかし上記装置では脱血不良が解消されたとき
に瞬時的に流量が増大したり、ハンチングを起し
て流量が不安定となることがあり、患者にとつて
危険な状態を招くことがあつた。(Problem that the invention aims to solve) However, with the above device, when the defective blood removal is resolved, the flow rate may increase instantaneously, or hunting may occur, causing the flow rate to become unstable, which may be harmful to the patient. This could lead to a dangerous situation.
したがつて本考案の目的は上記問題点を解消
し、長時間安定して呼吸補助を行うことのできる
人工補助肺装置を提供することである。 Therefore, an object of the present invention is to provide an artificial lung assist device which can solve the above problems and stably provide respiratory support for a long period of time.
（課題を解決するための手段）
上記目的を達成するためのこの考案の構成を第
１図に示す。(Means for Solving the Problem) The configuration of this invention for achieving the above object is shown in FIG.
血液体外循環回路１は、採血部H1から取り出
された血液を酸素加する人工肺２と、この人工肺
へ血液を送り込む血液ポンプ３を備え、浄化され
た血液を人工肺２を経て返血部H2より患者の体
内へ戻す。 The blood extracorporeal circulation circuit 1 includes an oxygenator 2 that oxygenates the blood taken out from the blood sampling section H1 , and a blood pump 3 that pumps blood to the oxygenator, and returns the purified blood through the oxygenator 2. Return to the patient's body from part H2 .
上記血液ポンプ３の上流側には圧力検知器４が
設けられている。１０は流量制御回路で、上記血
液ポンプ３を圧力検知器４で検知された圧力が下
限設定値を越えない範囲で、しかも流量の上限設
定値を越えない範囲で最大流量となるように回転
させる。 A pressure detector 4 is provided upstream of the blood pump 3. Reference numeral 10 denotes a flow rate control circuit, which rotates the blood pump 3 so that the maximum flow rate is achieved within a range in which the pressure detected by the pressure detector 4 does not exceed the lower limit set value and in a range that does not exceed the upper limit set value of the flow rate. .
（作用）
本考案は、血液ポンプの流量の上限値と脱血圧
力の下限値を予め設定しているため、例え採血部
が瞬間的に閉塞されて脱血不良状態となり異常な
脱血圧力となつたとしても異常圧力が解消された
ときに瞬時的に流量が増大することはなく、しか
も流量が一定でハンチングすることがないため長
時間安定に肺補助を行うことができる。(Function) This invention presets the upper limit of the flow rate of the blood pump and the lower limit of the evacuated blood pressure, so even if the blood sampling part becomes momentarily occluded, poor blood removal may occur, resulting in abnormal evacuated blood pressure. Even if the lung becomes cold, the flow rate will not increase instantaneously when the abnormal pressure is resolved, and the flow rate is constant and does not hunt, so lung support can be stably performed for a long period of time.
（実施例）
次に本考案装置の一実施例を図面にて説明す
る。第２図において、１は血液体外循環回路であ
る。採血部H1（シヤント、注射針などの通常の採
血器や貯血器などと連絡できる部分）から取り出
された患者の血液は血液ポンプ３により昇圧され
て人工肺２に入り、酸素加される。(Example) Next, an example of the device of the present invention will be described with reference to the drawings. In FIG. 2, 1 is an extracorporeal blood circulation circuit. The patient's blood taken out from the blood collection part H 1 (a part that can communicate with a normal blood collection device such as a shunt or a syringe needle or a blood storage device) is pressurized by the blood pump 3, enters the oxygenator 2, and is oxygenated.
上記人工肺２で酸素加された血液は気泡検知器
５を経て返血部H2（シヤントや点滴セツトなどに
連絡できる部分）から患者の体内へ戻される。 The blood oxygenated by the artificial lung 2 passes through the bubble detector 5 and is returned to the patient's body from a blood return section H2 (a section that can be connected to a shunt, an intravenous drip set, etc.).
上記人工肺２にはポリプロピレン、ポリスルホ
ン、シリコンなどからなる平板状、チユーブ状、
または中空繊維状のガス分離膜が収容されてい
る。通常は多数の中空繊維を収束してケーシング
に収容した中空糸型の人工肺が使用される。 The oxygenator 2 has a flat plate shape, a tube shape, etc. made of polypropylene, polysulfone, silicone, etc.
Alternatively, a hollow fiber gas separation membrane is housed. Usually, a hollow fiber type oxygenator is used, in which a large number of hollow fibers are bundled together and housed in a casing.
さらに、上記血液ポンプ３の上流側には膨張・
収縮可能なバルーンを硬い容器に収納したバルー
ン状のリザーバ６が設けられており、該リザーバ
の側壁にバルーンと容器で形成される空間の圧力
変化を検出して脱血圧力を検知する圧力検知器４
が取着されている。かかるバルーン状のリザーバ
を利用して圧力を検出する装置は、例えば実公昭
62−23488号などに記載されている。また血液循
環回路１の返血部H2の近傍には、気泡検知器５
が設けられている。 Furthermore, the upstream side of the blood pump 3 has an inflatable
A balloon-shaped reservoir 6 in which a deflated balloon is housed in a hard container is provided, and a pressure detector is provided on the side wall of the reservoir to detect pressure changes in the space formed by the balloon and the container to detect the withdrawal pressure. 4
is attached. A device that detects pressure using such a balloon-shaped reservoir is, for example, developed by Jikosho.
It is described in No. 62-23488, etc. In addition, an air bubble detector 5 is installed near the blood return section H2 of the blood circulation circuit 1.
is provided.
１０はマイクロコンピユータからなる流量制御
回路で、圧力設定回路１１からの圧力設定信号、
流量設定回路１２からの流量設定信号及び上記圧
力検知器４からの圧力検知信号を受けて比例微分
積分演算を行ない血液ポンプの流量が流量設定回
路１２で設定された血を上限とし、かつ脱血圧力
が圧力設定回路１１で設定された圧力範囲内であ
るという条件のもとで最大となるように制御す
る。 10 is a flow control circuit consisting of a microcomputer, which receives a pressure setting signal from a pressure setting circuit 11;
In response to the flow rate setting signal from the flow rate setting circuit 12 and the pressure detection signal from the pressure sensor 4, proportional differential and integral calculations are performed so that the flow rate of the blood pump is set at the upper limit of the blood set by the flow rate setting circuit 12, and the blood pressure is removed. The force is controlled to be maximum under the condition that the force is within the pressure range set by the pressure setting circuit 11.
この考案の装置は、第３図ａ，ｂに示す取付台
２０に取り付けられる。この取付台の前面には第
３図に示すように軟質塩化ビニルチユーブで形成
された血液体外循環回路１が装着され、該体外循
環回路の途中にバルーン状リザーバ６、血液ポン
プ３、人工肺２などが接続される。取付台の上部
には操作の指示等を表示する画面２１が配置され
ている。また取付台の下部前面には血液ポンプ２
が配置されている。２２はバルーン状リザーバ６
の圧力を検知する圧力検知器に接続されるチユー
ブである。上記血液循環回路１に接続された人工
肺２及びバルーン状チユーブ６はケーシング２３
内に収容されて、該ケーシング内に導入された加
温空気で体外循環血液を加温するようにしてい
る。 The device of this invention is mounted on a mount 20 shown in FIGS. 3a and 3b. As shown in FIG. 3, an extracorporeal blood circulation circuit 1 formed of a soft vinyl chloride tube is attached to the front of this mounting base, and a balloon-shaped reservoir 6, a blood pump 3, and an oxygenator 2 are installed in the middle of the extracorporeal circulation circuit. etc. are connected. A screen 21 for displaying operation instructions and the like is arranged at the top of the mounting base. In addition, there is a blood pump 2 on the bottom front of the mounting base.
is located. 22 is a balloon-shaped reservoir 6
This tube is connected to a pressure sensor that detects the pressure of The artificial lung 2 and the balloon-shaped tube 6 connected to the blood circulation circuit 1 are housed in a casing 23.
The heated air introduced into the casing heats extracorporeally circulating blood.
つぎに第２図の流量制御回路１０による制御に
ついて説明する。 Next, control by the flow rate control circuit 10 shown in FIG. 2 will be explained.
血液体外循環回路１は、予め生理食塩水のよう
なプライミング液を用いてプライミングがなされ
る。このプライミング完了後に、採血部H1と返
血部H2とが患者の血管に接続される。 The extracorporeal blood circulation circuit 1 is primed in advance using a priming liquid such as physiological saline. After this priming is completed, the blood collection section H1 and the blood return section H2 are connected to the patient's blood vessel.
スタート指令により血液ポンプ３が駆動して、
患者から取り出された血液を人工肺２へ送り、こ
こで酸素付加、二酸化炭素除去を行つた後患者に
戻される。 The blood pump 3 is driven by the start command,
Blood taken from the patient is sent to the artificial lung 2, where it is oxygenated and carbon dioxide removed, and then returned to the patient.
人工肺２には、オキシゲン・ブレンダー（図示
せず）から酸素ガスがガス回路を通じて供給され
る。バルーン状のリザーバ６は、ポリウレタン、
シリコンなどの生体適合性に優れた可撓性材料か
らなるバルーンを、ピリカーボネイト、アクリル
樹脂などの透明の非可撓性材料からなる容器に収
容したものであり、該容器とリザーバの間に密閉
空間を形成し、該密閉空間に導管を接続してその
端部に圧力検知器４が取着され、密閉空間には生
理食塩液が満たされている。血液ポンプ３は、血
液体外循環回路１をローラーでしごくローラー・
ポンプが使用される。そして、圧力設定回路１１
により設定された圧力信号を基準とし、上記圧力
検知器４からの信号を読取り、流量設定回路１２
により、血液ポンプ３の流量の上限を設定した状
態で、PID演算を行い、血液ポンプの流量が、流
量設定回路１２で設定された値を上限とし、かつ
該密閉空間の圧力が設定範囲内であるという条件
のもとで最大となるよう血液ポンプの回転数をコ
ントロールする。血液ポンプの起動／停止は、ポ
ンプ起動スイツチ（図示せず）により行い、特に
起動の際は急激に流量を上昇させず、遅延回路を
設けて漸次流量を上昇させることが好ましい。ま
た、血液回路の完全閉止などにより瞬時的に過度
の陰圧が生じ、流量制御回路１０による血液ポン
プのコントロールができない場合は、警報を発生
させて血液ポンプを停止させる。 Oxygen gas is supplied to the oxygenator 2 from an oxygen blender (not shown) through a gas circuit. The balloon-shaped reservoir 6 is made of polyurethane,
A balloon made of a flexible material with excellent biocompatibility such as silicone is housed in a container made of a transparent non-flexible material such as pyricarbonate or acrylic resin, and a seal is placed between the container and the reservoir. A space is formed, a conduit is connected to the sealed space, and a pressure sensor 4 is attached to the end of the conduit, and the sealed space is filled with physiological saline. The blood pump 3 is a roller that squeezes the blood extracorporeal circulation circuit 1 with a roller.
A pump is used. And the pressure setting circuit 11
The signal from the pressure detector 4 is read based on the pressure signal set by the flow rate setting circuit 12.
PID calculation is performed with the upper limit of the flow rate of the blood pump 3 set, and the flow rate of the blood pump is set to the value set in the flow rate setting circuit 12 as the upper limit, and the pressure of the sealed space is within the set range. The number of revolutions of the blood pump is controlled to the maximum under certain conditions. The blood pump is started/stopped by a pump start switch (not shown), and it is preferable that the flow rate not be increased suddenly during startup, but that a delay circuit be provided to gradually increase the flow rate. Further, if excessive negative pressure is instantaneously generated due to complete closure of the blood circuit and the blood pump cannot be controlled by the flow rate control circuit 10, an alarm is generated and the blood pump is stopped.
つぎに、上記血液ポンプの流量制御の詳細を第
４図に示すフローチヤートにしたがつて説明す
る。第４図のP1〜P7は制御の各ステツプを示す。
また略号Ｐは圧力検知器の圧力、Plimは圧力の
下限値、Psetは圧力設定値、Ｆは血液ポンプの回
転信号値、Fsetは血液ポンプの上限の流量設定値
を示す。 Next, details of the flow rate control of the blood pump will be explained according to the flowchart shown in FIG. 4. P1 to P7 in FIG. 4 indicate each step of control.
Further, the abbreviation P indicates the pressure of the pressure detector, Plim indicates the lower limit of the pressure, Pset indicates the pressure set value, F indicates the rotation signal value of the blood pump, and Fset indicates the upper limit flow rate set value of the blood pump.
まずP1で圧力の下限値Plim、流量の上限値
Fset及び圧力設定値Psetを設定する。P2で圧力
が下限の設定値より小さいか否かを判断し、圧力
が設定値より小さければ血液ポンプを停止してア
ラームを発生する。一方圧力が設定値より大きけ
ればP3で圧力検知器で検知された圧力が設定圧
力になつたか否かを判断する。圧力が設定値と一
致しなければP4に進み、ここで圧力が設定値よ
り大きいか否かを判断する。圧力が設定値より小
さければ血液ポンプの回転数を下げる。また圧力
が設定値より大きければP5で血液ポンプの回転
数を増大させる。次にP6でポンプの流量が設定
流量Fsetより大きいか否かを判断し、流量が上限
設定値より大きいとP7で流量を設定値に近づけ
るようにポンプの回転数を制御する。上記P1〜
P7をくり返して、血液ポンプの入口側の圧力が
上記圧力設定回路で設定された圧力の下限値を越
えない範囲で、しかも血液ポンプの流量が上記流
量設定回路で設定された上限値を越えない範囲で
最大流量となるようにコントロールする。 First, P1 is the lower limit value of pressure Plim and the upper limit value of flow rate.
Set Fset and pressure set value Pset. At P2, it is determined whether the pressure is lower than the lower limit set value, and if the pressure is lower than the set value, the blood pump is stopped and an alarm is generated. On the other hand, if the pressure is greater than the set value, it is determined in P3 whether the pressure detected by the pressure detector has reached the set pressure. If the pressure does not match the set value, the process proceeds to P4, where it is determined whether the pressure is greater than the set value. If the pressure is lower than the set value, reduce the rotation speed of the blood pump. Further, if the pressure is higher than the set value, the rotation speed of the blood pump is increased in P5. Next, in P6, it is determined whether the pump flow rate is larger than the set flow rate Fset, and if the flow rate is larger than the upper limit set value, the pump rotation speed is controlled in P7 so that the flow rate approaches the set value. Above P1~
Repeat P7 until the pressure on the inlet side of the blood pump does not exceed the lower limit of the pressure set in the above pressure setting circuit, and the flow rate of the blood pump does not exceed the upper limit set in the above flow rate setting circuit. Control the flow to the maximum within the range.
（考案の効果）
以上説明したように、患者の循環動態が変化
し、また患者が不用意に動くことによつて、カテ
ーテルが血管壁にくつついたり、血液体外循環回
路が折れ曲つて閉塞されるような事が発生し、血
液ポンプの吸引力により回路中に過度の陰圧を生
じることがあつた場合に、圧力設定回路により設
定された圧力信号を基準とし、圧力検知器からの
陰圧信号を読取り、流量設定回路により、血液ポ
ンプの流量の上限を設定した状態で、例えばPID
演算を行い、血液ポンプの流量が、流量設定回路
で設定した値を上限とし、かつバルーン状リザー
バの密閉空間の圧力が設定範囲内であるという条
件のもとで流量が最大となるように血液ポンプを
コントロールするため、安全に、しかも効率よく
治療を行うことができる。(Effects of the invention) As explained above, due to changes in the patient's hemodynamics and careless movement of the patient, the catheter may become stuck on the blood vessel wall or the extracorporeal blood circulation circuit may be bent and occluded. If an event such as this occurs and excessive negative pressure is generated in the circuit due to the suction force of the blood pump, the negative pressure from the pressure sensor is adjusted based on the pressure signal set by the pressure setting circuit. After reading the signal and setting the upper limit of the blood pump flow rate using the flow rate setting circuit, for example, PID
Calculation is performed to adjust the blood flow to the maximum under the conditions that the blood pump flow rate is the upper limit set by the flow rate setting circuit and the pressure in the sealed space of the balloon reservoir is within the set range. Since the pump is controlled, treatment can be performed safely and efficiently.
第１図及び第２図は本考案の人工補助肺装置の
フロー図であり、第３図ａ，ｂは同装置が取り付
けられる取付台を示す正面図と側面図であり、第
４図は同装置の作動を示すフローチヤートであ
る。
１……血液体外循環回路、２……人工肺、３…
…血液ポンプ、６……バルーン状リザーバ、１０
……流量設定回路、H1……採血部、H2……返血
部。
Figures 1 and 2 are flow diagrams of the artificial lung device of the present invention, Figures 3a and b are front and side views showing the mounting base on which the device is attached, and Figure 4 is the same. 3 is a flowchart showing the operation of the device. 1... Blood extracorporeal circulation circuit, 2... Artificial lung, 3...
...Blood pump, 6...Balloon-shaped reservoir, 10
...Flow rate setting circuit, H1 ...Blood collection section, H2 ...Blood return section.
Claims (1)
後、返血部から人体に戻す血液体外循環回路と、
上記血液体外循環回路に設けられて血液を人工肺
に送る血液ポンプとを含む人工補助肺装置におい
て、上記血液ポンプの入口側の圧力を検知する圧
力検知器と、上記血液ポンプの入口側の圧力の下
限値を設定する圧力設定回路と、上記血液ポンプ
の流量の上限値を設定する流量設定回路と、上記
圧力検知器からの信号を受けて、血液ポンプの入
口側の圧力が上記圧力設定回路で設定された圧力
の下限値を越えない範囲で、しかも血液ポンプの
流量が上記流量設定回路で設定された上限値を越
えない範囲で最大流量となるように血液ポンプの
流量を制御する流量制御回路とを備えたことを特
徴とする人工補助肺装置。 a blood extracorporeal circulation circuit that introduces blood from a blood collection section into an oxygenator for processing and then returns it to the human body from a blood return section;
An artificial lung apparatus including a blood pump provided in the extracorporeal blood circulation circuit to send blood to the oxygenator, comprising: a pressure detector for detecting the pressure on the inlet side of the blood pump; and a pressure detector for detecting the pressure on the inlet side of the blood pump. A pressure setting circuit sets the lower limit of the flow rate of the blood pump, a flow rate setting circuit sets the upper limit of the flow rate of the blood pump, and the pressure setting circuit sets the pressure on the inlet side of the blood pump in response to a signal from the pressure detector Flow rate control that controls the flow rate of the blood pump so that the maximum flow rate is achieved within a range that does not exceed the lower limit value of the pressure set in the above flow rate setting circuit, and within a range that does not exceed the upper limit value set by the flow rate setting circuit. An artificial lung apparatus characterized by comprising a circuit.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP1988003644U JPH0520334Y2 (en) | 1988-01-14 | 1988-01-14 |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP1988003644U JPH0520334Y2 (en) | 1988-01-14 | 1988-01-14 |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| JPH01110745U JPH01110745U (en) | 1989-07-26 |
| JPH0520334Y2 true JPH0520334Y2 (en) | 1993-05-27 |
Family
ID=31205462
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP1988003644U Expired - Lifetime JPH0520334Y2 (en) | 1988-01-14 | 1988-01-14 |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JPH0520334Y2 (en) |
Families Citing this family (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| SE510511C2 (en) * | 1997-12-16 | 1999-05-31 | Gambro Lundia Ab | System and method for monitoring a metering pump in a dialysis machine |
| US7022099B2 (en) * | 2003-03-17 | 2006-04-04 | Cardiovention, Inc. | Extracorporeal blood handling system with automatic flow control and methods of use |
| US20100143190A1 (en) * | 2008-12-04 | 2010-06-10 | Therox, Inc. | System for enriching a bodily fluid with a gas having occlusion detection capabilities |
Family Cites Families (2)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPS5287196U (en) * | 1975-12-25 | 1977-06-29 | ||
| JPS5290395U (en) * | 1975-12-27 | 1977-07-06 |
-
1988
- 1988-01-14 JP JP1988003644U patent/JPH0520334Y2/ja not_active Expired - Lifetime
Also Published As
| Publication number | Publication date |
|---|---|
| JPH01110745U (en) | 1989-07-26 |
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