JPS63143078A - Respiration supporting apparatus - Google Patents
Respiration supporting apparatusInfo
- Publication number
- JPS63143078A JPS63143078A JP61289557A JP28955786A JPS63143078A JP S63143078 A JPS63143078 A JP S63143078A JP 61289557 A JP61289557 A JP 61289557A JP 28955786 A JP28955786 A JP 28955786A JP S63143078 A JPS63143078 A JP S63143078A
- Authority
- JP
- Japan
- Prior art keywords
- blood
- circuit
- blood flow
- extracorporeal circulation
- alarm
- 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.)
- Granted
Links
- 230000029058 respiratory gaseous exchange Effects 0.000 title claims description 5
- 230000017531 blood circulation Effects 0.000 claims description 40
- 230000004087 circulation Effects 0.000 claims description 23
- 239000008280 blood Substances 0.000 claims description 19
- 210000004369 blood Anatomy 0.000 claims description 19
- 230000000241 respiratory effect Effects 0.000 claims description 18
- 230000000747 cardiac effect Effects 0.000 claims description 9
- 239000012528 membrane Substances 0.000 claims description 8
- 238000005096 rolling process Methods 0.000 claims description 6
- 210000003462 vein Anatomy 0.000 claims description 6
- 210000001367 artery Anatomy 0.000 claims description 5
- 230000002269 spontaneous effect Effects 0.000 claims description 4
- CURLTUGMZLYLDI-UHFFFAOYSA-N Carbon dioxide Chemical compound O=C=O CURLTUGMZLYLDI-UHFFFAOYSA-N 0.000 description 10
- 238000000034 method Methods 0.000 description 9
- 210000000056 organ Anatomy 0.000 description 7
- 230000007423 decrease Effects 0.000 description 6
- 210000004072 lung Anatomy 0.000 description 6
- 229910002092 carbon dioxide Inorganic materials 0.000 description 5
- 239000001569 carbon dioxide Substances 0.000 description 5
- 238000002618 extracorporeal membrane oxygenation Methods 0.000 description 4
- 239000007789 gas Substances 0.000 description 4
- 230000004217 heart function Effects 0.000 description 4
- MYMOFIZGZYHOMD-UHFFFAOYSA-N Dioxygen Chemical compound O=O MYMOFIZGZYHOMD-UHFFFAOYSA-N 0.000 description 3
- 206010019280 Heart failures Diseases 0.000 description 3
- QVGXLLKOCUKJST-UHFFFAOYSA-N atomic oxygen Chemical compound [O] QVGXLLKOCUKJST-UHFFFAOYSA-N 0.000 description 3
- 238000010586 diagram Methods 0.000 description 3
- 229910001882 dioxygen Inorganic materials 0.000 description 3
- 230000000694 effects Effects 0.000 description 3
- 230000006870 function Effects 0.000 description 3
- 229910052760 oxygen Inorganic materials 0.000 description 3
- 239000001301 oxygen Substances 0.000 description 3
- 230000000740 bleeding effect Effects 0.000 description 2
- 230000036772 blood pressure Effects 0.000 description 2
- 210000004556 brain Anatomy 0.000 description 2
- 210000003734 kidney Anatomy 0.000 description 2
- 210000004185 liver Anatomy 0.000 description 2
- 230000002093 peripheral effect Effects 0.000 description 2
- 238000009423 ventilation Methods 0.000 description 2
- 101100087414 Arabidopsis thaliana RH20 gene Proteins 0.000 description 1
- 241000283707 Capra Species 0.000 description 1
- 241000282994 Cervidae Species 0.000 description 1
- 206010009192 Circulatory collapse Diseases 0.000 description 1
- 208000002330 Congenital Heart Defects Diseases 0.000 description 1
- 206010012713 Diaphragmatic hernia Diseases 0.000 description 1
- 206010018910 Haemolysis Diseases 0.000 description 1
- 206010020772 Hypertension Diseases 0.000 description 1
- 206010059033 Neonatal aspiration Diseases 0.000 description 1
- XUIMIQQOPSSXEZ-UHFFFAOYSA-N Silicon Chemical compound [Si] XUIMIQQOPSSXEZ-UHFFFAOYSA-N 0.000 description 1
- 208000007536 Thrombosis Diseases 0.000 description 1
- 230000015572 biosynthetic process Effects 0.000 description 1
- 230000023555 blood coagulation Effects 0.000 description 1
- 230000036760 body temperature Effects 0.000 description 1
- 230000005794 circulatory dysfunction Effects 0.000 description 1
- 201000005890 congenital diaphragmatic hernia Diseases 0.000 description 1
- 208000028831 congenital heart disease Diseases 0.000 description 1
- 238000006114 decarboxylation reaction Methods 0.000 description 1
- 230000006837 decompression Effects 0.000 description 1
- 230000006866 deterioration Effects 0.000 description 1
- 238000000502 dialysis Methods 0.000 description 1
- 230000001605 fetal effect Effects 0.000 description 1
- 238000002695 general anesthesia Methods 0.000 description 1
- 230000000004 hemodynamic effect Effects 0.000 description 1
- 230000008588 hemolysis Effects 0.000 description 1
- 239000012510 hollow fiber Substances 0.000 description 1
- 230000009545 invasion Effects 0.000 description 1
- 230000007257 malfunction Effects 0.000 description 1
- 238000005259 measurement Methods 0.000 description 1
- 239000003158 myorelaxant agent Substances 0.000 description 1
- 244000144985 peep Species 0.000 description 1
- 206010040560 shock Diseases 0.000 description 1
- 229910052710 silicon Inorganic materials 0.000 description 1
- 239000010703 silicon Substances 0.000 description 1
- 238000002627 tracheal intubation Methods 0.000 description 1
- 210000002700 urine Anatomy 0.000 description 1
Abstract
(57)【要約】本公報は電子出願前の出願データであるた
め要約のデータは記録されません。(57) [Summary] This bulletin contains application data before electronic filing, so abstract data is not recorded.
Description
【発明の詳細な説明】
（産業上の利用分野）
本発明は膜型人工肺を用いた呼吸補助装置、特の呼吸補
助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 a respiratory assist device using a membrane oxygenator, and particularly to a respiratory assist device.
最近の膜型人工肺の開発の進歩は著しく、気泡型肺では
不可能だった体外循環による呼吸補助（ＥＣＭＯ）への
応用が可能になってきたｏＥＣＭＯは重篤な急性呼吸不
全、未熟児や新生児の胎児循環遣残症、羊水吸引、横隔
膜ヘルニア、先天性心疾患などに対する有力な治療手段
であるが、従来の靜動脈（Ｖ−Ａ）、靜靜脈（Ｖ−Ｖ
）のバイパス方式では生体に与える侵襲が大きく、かつ
ポンプを用いるため大がかりな装置を必要とし、患者の
維持管理にも多大の労力を要するという問題があった。Recent advances in the development of membrane oxygenators have made it possible to apply them to extracorporeal circulation respiratory support (ECMO), which was not possible with bubble lungs. It is an effective treatment method for neonatal fetal circulatory dysfunction, amniotic fluid aspiration, diaphragmatic hernia, congenital heart disease, etc.
) The bypass method has the problem that it is highly invasive to the living body, requires large-scale equipment because it uses a pump, and requires a great deal of effort to maintain and manage the patient.
これに対しＪ、 Ｔｈｏｒａｑ Ｃａｒｄｉｏｖａｓｃ
、 Ｓ町（ｒ５９５（１９７２）に開示された動静脈（
Ａ−Ｖ）バイパス法はカニュレーションが容易で生体に
与える侵襲が小さいという利点を有している。On the other hand, J. Thoraq Cardiovasc.
, Arteriovenous (arteriovenous) disclosed in S Town (r595 (1972))
A-V) The bypass method has the advantage of easy cannulation and minimal invasion to the living body.
また最近では膜型人工肺の高性能化に伴ないＡ−■バイ
パス方式を用い、自己心拍出で血液を環流させるボンプ
レス方式のＥＣＭＯも提案されている。Recently, as the performance of membrane oxygenators has improved, a bomb press type ECMO has also been proposed in which blood is perfused by the spontaneous cardiac output using the A-2 bypass method.
〔人工臓器１１，２８４（１９８２）、人工臓器ユ呈、
３５８（１９８３）、 医器学旦、１８６（１９８５
）など〕（発明が解決しようとする問題点）
自己心拍出によるＡ−Ｖバイパスによる呼吸補助は、手
技が簡便で、溶血も少なく、病室で容易に行なれるとい
う利点をもっているが、従来のＥＣＭＯでは体外循環血
流量の継時的な測定および体外循環血流量の変動に対す
る警報手段が具備されていないため実用上次のような問
題があった０すなわち血液の循環経路を増設する事にな
るため、心臓への負荷が増大し、血圧の尤進や心不全を
引きおこす恐れがある。患者が心不全をおこすと、必要
な体外循環血流量が安定して得られなくなシ、シかも体
外循環血流量が減りすぎると、膜型人工肺における血液
への酸素加量や、血液からの脱炭酸量が不足して呼吸補
助機能が低下し、患者の生命が危険にさらされる恐れが
ある。一方体外循環血流量が増えすぎると、脳、腎、肝
、肺などの体内の重要な諸臓器への循環血流量が低下し
、各臓器が機能不全を起したシ、手５足等の末梢での循
環不全を起す。[Artificial Organs 11, 284 (1982), Artificial Organs Presentation,
358 (1983), Igakudan, 186 (1985)
), etc.] (Problems to be Solved by the Invention) Respiratory support using A-V bypass using spontaneous cardiac output has the advantage of being a simple procedure, causing little hemolysis, and being easily performed in a hospital room. Since ECMO does not have a means to measure extracorporeal blood flow over time or to warn against changes in extracorporeal blood flow, it has the following practical problems: In other words, an additional blood circulation route is required. This increases the load on the heart, which can lead to increased blood pressure and heart failure. When a patient develops heart failure, the necessary extracorporeal circulation blood flow may not be stably obtained. There is a risk that the amount of decarboxylation will be insufficient and the respiratory support function will decline, putting the patient's life at risk. On the other hand, if the extracorporeal circulation blood flow increases too much, the circulation blood flow to important organs in the body such as the brain, kidneys, liver, and lungs decreases, resulting in malfunction of each organ and peripheral organs such as the hands and feet. This causes circulatory failure.
したがって、ポンプレスのＡ−Ｖバイパス螢こよる呼吸
補助を、長期にわたって実施する場合蚤こけ、特に体外
循環血流量をモニターし、血流量の過度な変動を警報す
ることはＡ−Ｖバイパス裔こよるＥＣＭＯを実施するた
めに絶対に必要である。本発明は上記機能を具備した呼
吸補助装置を提供することを目的としている。Therefore, when implementing pump-less AV bypass respiratory support for a long period of time, it is important to monitor fleas, especially extracorporeal circulation blood flow, and to warn of excessive fluctuations in blood flow. Absolutely necessary to implement ECMO. An object of the present invention is to provide a breathing assistance device having the above-mentioned functions.
（問題点を解決するための手段）
本発明装置は動脈と静脈をバイパスする体外循環回路回
路冬こ膜型人工肺を設けて自己心拍出で血液を還流させ
る呼吸補助装置であって、該体外循環血液回路を流れる
血流量を継時的に測定する血流測定手段と、該血流量測
定手段からの信号と設定回路で設定された血流量の上限
および／ｌたは下限値を比較して、血流量が設定値を外
れたときに信号を発信する比較回路と、該比較回路から
の信号を受けて警報を発する警報回路を具備してなる呼
吸補助装置である。(Means for Solving the Problems) The device of the present invention is a respiratory support device that is equipped with an extracorporeal circulation circuit that bypasses arteries and veins, and that circulates blood using spontaneous cardiac output. A blood flow measuring means that successively measures the blood flow flowing through the extracorporeal circulation blood circuit, and a signal from the blood flow measuring means is compared with the upper limit and /l or lower limit of the blood flow set in the setting circuit. This breathing assist device is equipped with a comparison circuit that issues a signal when the blood flow rate deviates from a set value, and an alarm circuit that issues an alarm upon receiving the signal from the comparison circuit.
（作 用）
ボンプレスのＡ−Ｖバイパスによる呼吸補助において、
最も危惧すべき問題は、動静脈との連結部や、裏型人工
肺内部における血栓形成と、それにともなう体外循環血
流量の減少、あるいは停止である。こうした部位におけ
る変化は潜在的に進行するために発見しにくいが体外循
環血液流量のモニターに下限警報を設定しておくと、容
易に検出できる。また患者の心機能の低下などに伴なう
体外循環流量の減少も所望のレベルで警報を発せられる
ため、生命に危険が及ぶような重大率に至る前に対策を
とる事ができる。(Function) In respiratory support using Bonpres's A-V bypass,
The most worrisome problem is thrombus formation at the arteriovenous connection or inside the back-type oxygenator, and the associated reduction or cessation of extracorporeal circulation blood flow. Changes in these areas are difficult to detect because they progress latently, but they can be easily detected by setting a lower limit alarm on the extracorporeal blood flow monitor. Furthermore, since a warning can be issued at a desired level for a decrease in the extracorporeal circulation flow due to a decline in the patient's cardiac function, countermeasures can be taken before the situation reaches a critical level that poses a life-threatening situation.
体外循環血液流量が下限値を割り、自己心拍による呼吸
補助が続行不可能になった場合は処理を中断する。また
必要なら体外循環回路にローリングチューブを取り付け
、このローリングチューブを直ちにポンプに組みこんで
、ポンプによるＶ−Ａ。If the extracorporeal circulation blood flow rate falls below the lower limit and it becomes impossible to continue respiratory support using the self-heartbeat, the process is interrupted. If necessary, attach a rolling tube to the extracorporeal circulation circuit, immediately incorporate this rolling tube into the pump, and perform VA using the pump.
またはＡ−Ｖバイパスに移行してもよい。Or you may shift to AV bypass.
上限警報が作動した場合には、体外循環回路に抵抗を付
与する事で体外循環血流量を適正レベルに戻すことがで
き、脳、腎、肝、肺などの主要臓器や、手足などの末梢
への血流量の不足を防止できる。また、接合部のゆるみ
、外れなどによる体外循環回路からの失血を検出するの
にも役立つ。When the upper limit alarm is activated, by adding resistance to the extracorporeal circulation circuit, the extracorporeal circulation blood flow can be returned to the appropriate level, and the blood flow is delivered to major organs such as the brain, kidneys, liver, and lungs, and to peripheral organs such as the limbs. can prevent insufficient blood flow. It is also useful for detecting blood loss from the extracorporeal circulation circuit due to loosening or dislodging of joints.
（実施例） 次に本発明装置の一実施例を図面にて説明する。(Example) Next, one embodiment of the device of the present invention will be described with reference to the drawings.
！ｓ１図は本発明装置のフロー図で′りシ、動脈と静脈
を膜型人工肺２を介してバイパスする体外循環血液回路
１と該血液回路内を流れる血流量を測定する血流量測定
手段３と、血流量の上限および／または下限を設定する
回路４と、該血流量測定手段３と設定回路４からの信号
を比較して、血流量が設定値を外れたときに信号を出す
比較回路５と、該比較回路からの信号を受けて警報を発
する警報回路６で構成されている。! Figure s1 is a flow diagram of the device of the present invention, which includes an extracorporeal circulation blood circuit 1 that bypasses arteries and veins via a membrane oxygenator 2, and a blood flow measuring means 3 that measures the blood flow flowing through the blood circuit. a circuit 4 for setting the upper and/or lower limits of blood flow, and a comparison circuit that compares the signals from the blood flow measuring means 3 and the setting circuit 4 and outputs a signal when the blood flow deviates from the set value. 5, and an alarm circuit 6 which receives a signal from the comparison circuit and issues an alarm.
膜型人工肺２は公知の人工肺、通常中空糸型の人工肺が
用いられる。As the membrane oxygenator 2, a known oxygenator, usually a hollow fiber oxygenator, is used.
血流量測定手段３としては、電磁血量計、超音波血流計
などの公知の血流針を用いることができる。As the blood flow measuring means 3, a known blood flow needle such as an electromagnetic blood flow meter or an ultrasonic blood flow meter can be used.
血流量設定回路４では下限を患者の心拍出量００〜４０
％、好ましくは５〜３５％の範囲内に設定する０症例に
よっても異なるが上記範囲で十分な呼吸補助効果が得ら
れる。上限は心拍出量の１０％〜８０％１好ましくは１
５チ〜５ｏチの範囲に設定しておく事により重篤な心不
全の発生、完遂を防止する事が可能である。この範囲内
の体外循環流量下で、もし血液への酸素加能力が不足す
る時は、生体肺への持続陽圧呼吸法（ＣＰＡＰ ）や、
呼気終末障王法（ＰＥＥＰ）などの人工換気法を併用す
る事が望ましい。また、もし炭酸ガス除去が不足するよ
うであれば、脱型人工肺へのガス流量を増加させる事に
よって、炭酸ガス除去量を増加させられる。The blood flow setting circuit 4 sets the lower limit to the patient's cardiac output of 00 to 40.
%, preferably within the range of 5 to 35%. Although it varies depending on the case, a sufficient respiratory support effect can be obtained within the above range. The upper limit is 10% to 80% of cardiac output, preferably 1
By setting it within the range of 5 to 5 degrees, it is possible to prevent the occurrence and completion of serious heart failure. Under extracorporeal circulation flow rates within this range, if the ability to add oxygen to the blood is insufficient, continuous positive airway pressure (CPAP) to the living lungs,
It is desirable to use artificial ventilation methods such as end-expiratory ventilation (PEEP). Furthermore, if carbon dioxide removal is insufficient, the amount of carbon dioxide gas removed can be increased by increasing the gas flow rate to the demolding oxygenator.
警報回路６は光、音等の公知の警報手段を利用できる。The alarm circuit 6 can utilize known alarm means such as light and sound.
通常音によるものが最もわかシ易く好ましい。無線方式
により警報を看護婦詰所などに伝達、表示する方式も便
利である。It is preferable to use normal sound because it is easiest to understand. It is also convenient to transmit and display the alarm to a nurse's office or the like using a wireless method.
呼吸補助をさらに精密に制御するために上記装置に、さ
らに血液ガス濃度（Ｏｚ、ＣＯｚλ血液ＰＨ％心機能、
循環動態、呼吸状態、尿量、体温などの各種連続モニタ
ー類を具備してもよい。また、患者の出血をモニターし
、出血時には警報を発する漏血センサーなどの併用も実
際的である。In order to control respiratory support more precisely, the above device is further equipped with blood gas concentration (Oz, COzλ, blood PH%, cardiac function,
Various continuous monitors such as hemodynamics, respiratory status, urine output, and body temperature may be provided. It is also practical to use a blood leakage sensor that monitors the patient's bleeding and issues an alarm in the event of bleeding.
上記装置で自己心拍による呼吸補助が続行できなくなっ
たときに、直ちにポンプでＶ−ＡまたはＡ−Ｖバイパス
に移行すれば安全に呼吸補助を続行できる。そのため血
液回路１にはロー２ポンプの取シ付は可能なローリング
チューブ７を設けておくことが好ましい。かかるローリ
ングチューブは人工肺の動脈側または静脈側どちらに取
シ付けてもよい。通常静脈側層こ取シ付けられる。When the above-mentioned device becomes unable to continue respiratory support using the patient's own heartbeat, the pump can immediately switch to VA or A-V bypass to safely continue respiratory support. Therefore, it is preferable to provide the blood circuit 1 with a rolling tube 7 to which the Row 2 pump can be attached. Such a rolling tube may be attached to either the arterial or venous side of the oxygenator. Usually attached to the venous layer.
次に上記装置を用いた実験例について説明する。Next, an experimental example using the above device will be explained.
シバヤギ（体］ｉ１．５ｋｐ、生後３時間）に筋弛緩剤
併用全身麻酔を行い、気管内挿管した。８Ｆｒのクラレ
社展シンウオールカテーテルをｙ！ｓ帯動脈および同静
脈に各一本挿入し、第２図に示すように腰帯動脈、電磁
血流計３、膜型肺（シリコンコート膜）２、腰帯静脈を
連結して体外循環血液回路ｌを形成した。A deer goat (body size: i1.5 kp, 3 hours after birth) was given general anesthesia combined with a muscle relaxant and endotracheally intubated. 8Fr Kuraray Exhibition Thin Wall Catheter! One each is inserted into the s-band artery and the same vein, and as shown in Figure 2, the lumbar artery, electromagnetic blood flow meter 3, membrane type lung (silicon coated membrane) 2, and lumbar vein are connected to create an extracorporeal circulation blood circuit l. was formed.
電磁血流計３の下限を心拍出量の１０％、上限を同４５
チに設定後、ボンブレスＡＶバイパス方式による呼吸補
助を行った。人工肺（０，２５ｔ／）に酸素１ｔ／ｍｉ
ｎを流したところ、生体の炭酸ガス分圧は約３３ｓａｗ
Ｈ！？と低く、良好な水準を維持できたが、酸素ガス分
圧は約３５■Ｈｐと低かったので持続的陽圧呼吸法（Ｃ
ＰＡＰ）を併用する事とし％ ５ｃ！ＲＨ２０の陽圧酸
素を気管内挿管チューブに投入した。１０分後に生体の
酸素ガス分圧は１５０鴎ＨＰ以上に上昇し、以降高水準
を維持し得た。この時の生体の炭酸ガス分圧は３０ｗＨ
ｆで良好だった。The lower limit of electromagnetic blood flow meter 3 is 10% of cardiac output, and the upper limit is 45% of cardiac output.
After setting the patient to 1, breathing assistance was performed using the bombless AV bypass method. Oxygen 1t/mi in artificial lung (0,25t/)
When flowing n, the partial pressure of carbon dioxide in the living body was about 33 saw.
H! ? However, since the partial pressure of oxygen gas was low at approximately 35 HP, continuous positive airway pressure (C) was applied.
PAP) should be used in combination with % 5c! Positive pressure oxygen at RH20 was administered to the endotracheal intubation tube. After 10 minutes, the oxygen gas partial pressure of the living body rose to more than 150 HP, and was able to maintain a high level thereafter. At this time, the partial pressure of carbon dioxide in the living body is 30wH
It was good at f.
約１８時間後、血流計の下限警報が鳴った。これは別に
取りつけておいた心機能分析用ポリグラフ、および血圧
モニターより、心拍数の減少、血圧の若干の低下と認め
、予め血液循環回路１の屓帯靜脈側にとりつけておいた
ローリングチューブ７を第３図に示すように透析用血液
ポンプ１０１こ取シ付け、かつ除圧モニター１１を設置
して、Ｖ−Ａバイパスで体外循環を再開した。以降５時
間にわたシ体外循環血流量は心拍出量の約４０％を安定
に維持することができて、血液ガスも炭酸ガス分圧２６
■Ｈｅ、酸素ガス分圧２４０■Ｈ２と良好で、安定した
呼吸補助効果が得られた。Approximately 18 hours later, the blood flow meter's low limit alarm sounded. A polygraph for cardiac function analysis and a blood pressure monitor installed separately confirmed that this was a decrease in heart rate and a slight decrease in blood pressure, and the rolling tube 7, which had been attached in advance to the ligamentary vein side of the blood circulation circuit 1, was inserted. As shown in FIG. 3, a dialysis blood pump 101 was installed, a decompression monitor 11 was installed, and extracorporeal circulation was resumed using the VA bypass. Over the next 5 hours, the extracorporeal circulation blood flow was able to stably maintain approximately 40% of the cardiac output, and the blood gas also had a partial pressure of carbon dioxide of 26%.
■He, oxygen gas partial pressure was good with 240■H2, and a stable respiratory support effect was obtained.
（発明の効果）
以上に述べたように、本発明装置は体外循環回路内での
血液の凝固、漏出や、患者の心機能低下に優れた安全な
ボンブレス方式による呼吸補助装置である。(Effects of the Invention) As described above, the device of the present invention is a safe bombless respiratory support device that is excellent in preventing blood coagulation and leakage in the extracorporeal circulation circuit and in preventing deterioration of the patient's cardiac function.
第１図は本発明装置のフロー図であり、第２図及び第３
図は本発明装置を用いた実験例を示すフロー図である。
１・・・・・・・・・体外循環血液回路２・・・・・・
・・・脱型人工肺
３・・・・・・・・・血流量測定手段
４・・・・・・・・・設定回路
５・・・・・・・・・比較回路
６・・・・・・・・二警報回路FIG. 1 is a flow diagram of the device of the present invention, and FIGS.
The figure is a flow diagram showing an experimental example using the apparatus of the present invention. 1... Extracorporeal circulation blood circuit 2...
... Demolding oxygenator 3 ... Blood flow measurement means 4 ... Setting circuit 5 ... Comparison circuit 6 ... ...Second alarm circuit
Claims (1)
人工肺を設けて自己心拍出で血液を還流させる呼吸補助
装置であつて、該体外循環血液回路を流れる血流量を継
時的に測定する血流量測定手段と、該血流量測定手段か
らの信号と設定回路で設定された血流量の上限値および
／または下限値を比較して、血流量が設定値から外れた
ときに信号を発信する比較回路と、該比較回路からの信
号を受けて警報を発する警報回路を具備してなる呼吸補
助装置。 ２、該体外循環血液回路にローラポンプ取着用のローリ
ングチューブが設けられてなる特許請求の範囲第１項記
載の呼吸補助装置。[Scope of Claims] 1. A respiratory support device that includes a membrane oxygenator in an extracorporeal blood circulation circuit that bypasses arteries and veins, and that circulates blood using spontaneous cardiac output, the blood flowing through the extracorporeal circulation blood circuit. A blood flow measuring means that measures the flow rate over time compares the signal from the blood flow measuring means with the upper limit and/or lower limit of the blood flow set in the setting circuit, and determines whether the blood flow is from the set value. A breathing assistance device comprising a comparison circuit that sends out a signal when a disconnection occurs, and an alarm circuit that issues an alarm upon receiving the signal from the comparison circuit. 2. The respiratory assistance device according to claim 1, wherein the extracorporeal circulation blood circuit is provided with a rolling tube for attaching a roller pump.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP61289557A JPS63143078A (en) | 1986-12-03 | 1986-12-03 | Respiration supporting apparatus |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP61289557A JPS63143078A (en) | 1986-12-03 | 1986-12-03 | Respiration supporting apparatus |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| JPS63143078A true JPS63143078A (en) | 1988-06-15 |
| JPH0478312B2 JPH0478312B2 (en) | 1992-12-10 |
Family
ID=17744777
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP61289557A Granted JPS63143078A (en) | 1986-12-03 | 1986-12-03 | Respiration supporting apparatus |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JPS63143078A (en) |
Cited By (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| WO2016027868A1 (en) * | 2014-08-20 | 2016-02-25 | 泉工医科工業株式会社 | Blood circulation system |
| WO2016027866A1 (en) * | 2014-08-20 | 2016-02-25 | 泉工医科工業株式会社 | Blood circulation system |
| WO2016027852A1 (en) * | 2014-08-20 | 2016-02-25 | 泉工医科工業株式会社 | Blood circulation system |
| WO2017115487A1 (en) * | 2015-12-28 | 2017-07-06 | テルモ株式会社 | Cardiac function measurement system and extracorporeal circulation device provided with cardiac function measurement system |
Citations (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPS53101893A (en) * | 1977-02-18 | 1978-09-05 | Iriyou Kougaku Kenkiyuushiyo K | Device for supervising artificial dialysis |
| JPS55106829U (en) * | 1979-01-22 | 1980-07-25 | ||
| JPS60210721A (en) * | 1984-04-04 | 1985-10-23 | Kawasumi Lab Inc | Disposable flowrate measuring apparatus for medical treatment |
-
1986
- 1986-12-03 JP JP61289557A patent/JPS63143078A/en active Granted
Patent Citations (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPS53101893A (en) * | 1977-02-18 | 1978-09-05 | Iriyou Kougaku Kenkiyuushiyo K | Device for supervising artificial dialysis |
| JPS55106829U (en) * | 1979-01-22 | 1980-07-25 | ||
| JPS60210721A (en) * | 1984-04-04 | 1985-10-23 | Kawasumi Lab Inc | Disposable flowrate measuring apparatus for medical treatment |
Cited By (12)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| WO2016027868A1 (en) * | 2014-08-20 | 2016-02-25 | 泉工医科工業株式会社 | Blood circulation system |
| WO2016027866A1 (en) * | 2014-08-20 | 2016-02-25 | 泉工医科工業株式会社 | Blood circulation system |
| WO2016027852A1 (en) * | 2014-08-20 | 2016-02-25 | 泉工医科工業株式会社 | Blood circulation system |
| JP2016043256A (en) * | 2014-08-20 | 2016-04-04 | 泉工医科工業株式会社 | Blood circulation system |
| JP2016043259A (en) * | 2014-08-20 | 2016-04-04 | 泉工医科工業株式会社 | Blood circulation system |
| EP3167920A4 (en) * | 2014-08-20 | 2017-08-02 | Senko Medical Instrument Mfg. Co., Ltd. | Blood circulation system |
| US10751463B2 (en) | 2014-08-20 | 2020-08-25 | Senko Medical Instrument Mfg. Co., Ltd. | Blood circulation system |
| US10786617B2 (en) | 2014-08-20 | 2020-09-29 | Senko Medical Instrument Mfg. Co., Ltd. | Blood circulation system |
| US11040132B2 (en) | 2014-08-20 | 2021-06-22 | Senko Medical Instrument Mfg. Co., Ltd. | Blood circulation system |
| US11141519B2 (en) | 2014-08-20 | 2021-10-12 | Senko Medical Instrument Mfg. Co., Ltd. | Blood circulation system |
| WO2017115487A1 (en) * | 2015-12-28 | 2017-07-06 | テルモ株式会社 | Cardiac function measurement system and extracorporeal circulation device provided with cardiac function measurement system |
| JPWO2017115487A1 (en) * | 2015-12-28 | 2018-10-18 | テルモ株式会社 | Cardiac function measurement system and extracorporeal circulation apparatus including the cardiac function measurement system |
Also Published As
| Publication number | Publication date |
|---|---|
| JPH0478312B2 (en) | 1992-12-10 |
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Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| LAPS | Cancellation because of no payment of annual fees |