JPS639320Y2 - - Google Patents
Info
- Publication number
- JPS639320Y2 JPS639320Y2 JP1981137476U JP13747681U JPS639320Y2 JP S639320 Y2 JPS639320 Y2 JP S639320Y2 JP 1981137476 U JP1981137476 U JP 1981137476U JP 13747681 U JP13747681 U JP 13747681U JP S639320 Y2 JPS639320 Y2 JP S639320Y2
- Authority
- JP
- Japan
- Prior art keywords
- signal
- blood
- pressure
- dialysate
- flow path
- 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
Links
- 239000008280 blood Substances 0.000 claims description 30
- 210000004369 blood Anatomy 0.000 claims description 30
- 230000036772 blood pressure Effects 0.000 claims description 27
- 238000005070 sampling Methods 0.000 claims description 27
- 230000010349 pulsation Effects 0.000 claims description 13
- 210000003734 kidney Anatomy 0.000 claims description 11
- 230000017531 blood circulation Effects 0.000 claims description 6
- 239000012528 membrane Substances 0.000 claims description 5
- 238000000502 dialysis Methods 0.000 claims description 4
- 239000012530 fluid Substances 0.000 claims description 2
- 238000005259 measurement Methods 0.000 description 10
- 239000007788 liquid Substances 0.000 description 5
- 238000010586 diagram Methods 0.000 description 4
- 238000006243 chemical reaction Methods 0.000 description 2
- 230000000737 periodic effect Effects 0.000 description 2
- 230000004043 responsiveness Effects 0.000 description 2
- 210000001367 artery Anatomy 0.000 description 1
- 238000000034 method Methods 0.000 description 1
- 210000003462 vein Anatomy 0.000 description 1
Landscapes
- Measuring Pulse, Heart Rate, Blood Pressure Or Blood Flow (AREA)
- External Artificial Organs (AREA)
Description
【考案の詳細な説明】
本考案は、血液圧力測定部が改良された人工腎
臓装置に関する。[Detailed Description of the Invention] The present invention relates to an artificial kidney device with an improved blood pressure measuring section.
第１図は、従来の人工腎臓装置の主要部の構成
説明図である。装置は、ダイアライザー（透析
器）１の膜の一方の室を含む流路系であつて、血
液ポンプ２、動脈側チヤンバー３、チヤンバー３
に設けられ、流路系の圧力を検出する圧力計４、
流路系の圧力を調節する絞り弁（オートクレン
メ）５及び静脈側チヤンバー６を有する血液系
と、ダイヤライザ１の膜の他方の室を含む流路系
であつて、透析液貯留槽８、送液ポンプ９及び流
路の圧力を検出する圧力計１０とを有する透析液
系と、測定端としての圧力計４及び１０からの信
号夫々の平均値を求め、２つの信号の減算をし、
その差に対応する信号を出力する演算部１１及び
その出力信号を測定値とし、所定の演算をして、
操作端である絞り弁５に制御信号を出力する調節
部１２を有する制御系とから成る。前記演算部１
１が、その初段に平均値演算手段を有するのは、
圧力計４からの信号、即ち、血液圧力が、後述す
る理由によつて、第３Ａ図、又は、第３Ｂ図に示
すように、周期をもつた脈動現象を有するためで
ある。 FIG. 1 is an explanatory diagram of the configuration of the main parts of a conventional artificial kidney device. The device is a flow path system including one chamber of a membrane of a dialyzer 1, a blood pump 2, an arterial side chamber 3, and a chamber 3.
a pressure gauge 4 installed in the flow path system to detect the pressure in the flow path system;
A flow path system including a blood system having a throttle valve (auto-cleaner) 5 for adjusting the pressure of the flow path system and a venous chamber 6, and the other chamber of the membrane of the dialer 1, and a dialysate storage tank 8, A dialysate system having a liquid pump 9 and a pressure gauge 10 that detects the pressure in the flow path, and the average value of the signals from the pressure gauges 4 and 10 as measurement ends are determined, and the two signals are subtracted,
A calculation unit 11 outputs a signal corresponding to the difference, and the output signal is used as a measurement value, and a predetermined calculation is performed,
The control system includes an adjustment section 12 that outputs a control signal to the throttle valve 5, which is an operating end. The arithmetic unit 1
1 has an average value calculation means in its first stage because
This is because the signal from the pressure gauge 4, that is, the blood pressure, has a periodic pulsation phenomenon, as shown in FIG. 3A or 3B, for reasons described later.
上記血液系は、患者１３の動脈からの血液が、
血液ポンプ２によつて、チヤンバー３→ダイアラ
イザ１→絞り弁５→チヤンバー６を経て、患者１
３の静脈に戻されるようになつている。又、透析
液系は、透析液貯留槽８の透析液が、送液ポンプ
９によつて、ダイアライザ１内にて、膜を介して
血液と反対方向に流れ、排出されるようになつて
いる。一方、制御系は、圧力計４の信号と圧力計
１０の信号との差、即ち、血液系の血液圧力と透
析液系の液圧力（ほとんど一定値を示している）
との差が、所定の範囲に入るように、絞り弁５を
調節するようになつている。 In the blood system, blood from patient 13's artery is
Blood pump 2 passes chamber 3 → dialyzer 1 → throttle valve 5 → chamber 6 to patient 1.
It is designed to be returned to the 3rd vein. In addition, the dialysate system is configured such that the dialysate in the dialysate storage tank 8 flows in the opposite direction to the blood through the membrane in the dialyzer 1 by a liquid pump 9 and is discharged. . On the other hand, the control system controls the difference between the signal of the pressure gauge 4 and the signal of the pressure gauge 10, that is, the blood pressure of the blood system and the fluid pressure of the dialysate system (which shows almost constant values).
The throttle valve 5 is adjusted so that the difference between the two is within a predetermined range.
第２図は、上記装置に用いられる血液ポンプ２
の主要部の構成説明図である。血液ポンプ２は、
円筒状の壁１４に設置されるチユーブ１５と、チ
ユーブ１５を壁面に押圧してしごきながら回転す
るローラ１６と、ローラ１６を回転駆動するモー
タ（図示せず）を有し、ローラ１６の回転によつ
てチユーブ１５内の血液を移送するようになつて
いる。このため、ローラ１６がチユーブ１５に接
触する時及びチユーブ１５から離れる時、血流に
圧力変動を与えることになる。そして、この圧力
変動は、ポンプ２（ローラ１６）が高速回転にな
れば、第３Ａ図の波形P1のように、短い周期T1
の脈動となり、低速回転になれば、第３Ｂ図の波
形P2のように、長い周期T2の脈動となる。 FIG. 2 shows a blood pump 2 used in the above device.
FIG. Blood pump 2 is
It has a tube 15 installed on a cylindrical wall 14, a roller 16 that rotates while pressing the tube 15 against the wall surface, and a motor (not shown) that rotationally drives the roller 16. Therefore, the blood within the tube 15 is transferred. Therefore, when the roller 16 comes into contact with the tube 15 and when it leaves the tube 15, pressure fluctuations are imparted to the blood flow. If the pump 2 (roller 16) rotates at high speed, this pressure fluctuation will have a short cycle T 1 as shown in the waveform P 1 in FIG. 3A.
When the rotation speed is low, the pulsation becomes a pulsation with a long period T 2 as shown by the waveform P 2 in FIG. 3B.
人工腎臓装置の血液系において、上記のよう
な、周期の異なる圧力変動は、頻繁に起り得る。
何故ならば、人工腎臓装置における血液流量は、
患者の体調や年令に応じて決定される。即ち、透
析を受ける患者個々に、血液ポンプ２の回転数が
設定される。それ故、その都度、血液系における
血液圧力の変動周期（脈動周期）が変る。 In the blood system of an artificial kidney device, pressure fluctuations with different periods as described above can occur frequently.
This is because the blood flow rate in an artificial kidney device is
It is determined according to the patient's physical condition and age. That is, the rotation speed of the blood pump 2 is set for each patient undergoing dialysis. Therefore, the fluctuation period (pulsation period) of blood pressure in the blood system changes each time.
したがつて、上記のように、前記制御系におけ
る演算部には、脈動信号の平均値が入力される構
成となつている。 Therefore, as described above, the average value of the pulsation signals is input to the calculation section in the control system.
ところで、昨今、前記制御系は、コンピユータ
等を中心とした回路で構成される機会が多くなつ
てきた。この場合、血液圧力信号及び透析液圧力
信号は、特定の周期の信号でサンプリングされた
後、デイジタル信号に変換され、入力される。サ
ンプリング方式において、測定信号が、上記血液
圧力信号のように、周期が血圧ポンプ２の回転数
設定によつて変る場合、通常、サンプリング信号
の周波数は、最も短い周期の測定信号に合せて選
定される。即ち、サンプリング信号は、測定信号
の最大周波数より極めて高い周波数を有するもの
となる。しかし、サンプリング周波数を高くする
と、周期の長い測定信号（第３Ｂ図のような低周
波信号）を入力とした場合、必要以上のサンプリ
ングをすることになり、その後のデータ処理が繁
雑になるばかりか、定めた時間内の平均値を求め
るにも、演算時間が長くなつて、応答性が悪くな
る。逆に、サンプリング周波数を低くすると、平
均値を正確に得ることができない。 Incidentally, in recent years, the control system is increasingly composed of circuits centered on computers and the like. In this case, the blood pressure signal and the dialysate pressure signal are sampled with signals of a specific period, and then converted into digital signals and input. In the sampling method, when the period of the measurement signal changes depending on the rotation speed setting of the blood pressure pump 2, like the blood pressure signal mentioned above, the frequency of the sampling signal is usually selected according to the measurement signal with the shortest period. Ru. That is, the sampling signal has a frequency much higher than the maximum frequency of the measurement signal. However, if the sampling frequency is increased, if a measurement signal with a long period (low frequency signal as shown in Figure 3B) is input, more sampling will be required than necessary, which will not only make subsequent data processing more complicated. Even if the average value within a predetermined period of time is calculated, the calculation time becomes long and the responsiveness deteriorates. Conversely, if the sampling frequency is lowered, the average value cannot be obtained accurately.
本考案は、前記人工腎臓装置において、血液ポ
ンプによる圧力変動を含む血液圧力信号から、そ
の平均値を正確、かつ、応答性よく求めることが
できるようにすることにある。 The present invention is to enable the artificial kidney device to accurately and responsively determine the average value from a blood pressure signal including pressure fluctuations caused by a blood pump.
本考案の構成は、前記人工腎臓装置において、
血液ポンプの回転数を検出する回転計と、後出の
演算・制御部から与えられる一定周波数のサンプ
リング信号によつて前記透析液流路の血液圧力信
号をサンプリングし、同じくこの演算・制御部か
ら与えられる、前記回転計の出力信号の周波数に
対応するサンプリング信号によつて前記透析液流
路の透析液圧力信号をサンプリングし、これらを
デイジタル変換するＡ／Ｄ変換部と、前記回転計
からの出力信号、及び前記Ａ／Ｄ変換部からの出
力信号が与えられ、前記透析液圧力信号サンプリ
ング用の一定周波数のサンプリング信号、及び前
記血液圧力信号サンプリング用の前記回転計の出
力信号の周波数に対応したサンプリング信号を前
記Ａ／Ｄ変換部に与え、前記血液圧力の脈動周期
を演算時間として前記血液圧力信号の平均値を求
め、前記透析液圧力信号の平均値との差を演算
し、前記血液流路と透析液流路との間の圧力を制
御する信号として出力する演算・制御部とを設け
たことにある。 The configuration of the present invention is such that in the artificial kidney device,
The blood pressure signal in the dialysate flow path is sampled by a tachometer that detects the number of rotations of the blood pump and a sampling signal of a constant frequency given from a calculation/control unit, which will be described later. an A/D converter that samples the dialysate pressure signal in the dialysate flow path using a sampling signal corresponding to the frequency of the output signal of the tachometer, and converts the dialysate pressure signal into digital; An output signal and an output signal from the A/D converter are provided and correspond to a constant frequency sampling signal for sampling the dialysate pressure signal and a frequency of the output signal of the tachometer for sampling the blood pressure signal. The obtained sampling signal is applied to the A/D converter, the average value of the blood pressure signal is determined using the pulsation period of the blood pressure as the calculation time, and the difference from the average value of the dialysate pressure signal is calculated. The present invention includes a calculation/control unit that outputs a signal for controlling the pressure between the flow path and the dialysate flow path.
以下、図面を参照し、本考案について説明す
る。 The present invention will be described below with reference to the drawings.
第４図は、本考案の実施例装置の構成説明図
で、第４図において、第１図に付した符号と同一
のものは、同一意味で用いられており、こゝでの
説明を省略する。 FIG. 4 is an explanatory diagram of the configuration of an embodiment of the present invention. In FIG. 4, the same reference numerals as in FIG. do.
１７は血液ポンプ２のモータの回転数を検出す
る回転計、１８はアナログ・デイジタル変換部
（Ａ／Ｄ変換部）、１９はCPUを中心とした演
算・制御部である。Ａ／Ｄ変換部１８は、演算・
制御部１９からの信号S5によつて、圧力計４の出
力信号S1のサンプリングを行い、デイジタル変換
をして、信号S3を出力すると共に、信号S6によつ
て、圧力計１０の出力信号S2のサンプリングを行
い、デイジタル変換をして、信号S4を出力する機
能を有する。演算・制御部１９は、回転計１７の
出力信号S7の周波数を函数とするサンプリング信
号S5及び内部発振器に基づく周波数のサンプリン
グ信号S6を出力する機能と、信号S7の周期に対応
する時間を演算時間とし、信号S3の平均値算出演
算をする機能と、上記演算時間とは独立した演算
時間で、信号S4の平均値算出演算をする機能と、
信号S3の平均値と信号S4の平均値の減算をする機
能と、該減算の差を測定信号とし、所定の演算を
して絞り弁５に操作信号S8を出力する機能を有し
ている。 17 is a tachometer that detects the rotation speed of the motor of the blood pump 2; 18 is an analog/digital converter (A/D converter); and 19 is an arithmetic/control unit centered on the CPU. The A/D converter 18 performs calculations and
The output signal S 1 of the pressure gauge 4 is sampled by the signal S 5 from the control unit 19, digitally converted, and outputted as the signal S 3 . It has the function of sampling the output signal S2 , digitally converting it, and outputting the signal S4 . The calculation/control unit 19 has a function of outputting a sampling signal S 5 whose frequency is a function of the output signal S 7 of the tachometer 17 and a sampling signal S 6 whose frequency is based on an internal oscillator, and a function corresponding to the period of the signal S 7 . A function to calculate the average value of the signal S 3 using time as the calculation time, a function to calculate the average value of the signal S 4 with a calculation time independent of the calculation time,
It has a function of subtracting the average value of the signal S3 and the average value of the signal S4 , and a function of using the difference between the subtractions as a measurement signal, performing a predetermined calculation, and outputting an operation signal S8 to the throttle valve 5. ing.
次に、上記装置の動作について説明する。 Next, the operation of the above device will be explained.
透析を始めるにあたつて、血液ポンプ２は、患
者１３の体調等に合せて回転数が設定される。
又、送液ポンプ９も、所定の値に設定される。そ
して、透析中、血液ポンプ２及び送液ポンプ９に
よつて、所定の血液流量及び透析液流量が得られ
る。この時の圧力信号S1及び回転数信号S7は、第
５図に示すように、血液ポンプ２の回転数（回転
速度）によつて、脈動周期を異にする。第５図に
おいて、信号S1a及びS7aは、高速回転時の圧力信
号S1の脈動部分（周期＝T1）及び回転数信号S7
であり、信号S1b及びS7bは、低速回転時の圧力信
号S1の脈動部分（周期＝T2＞T1）及び回転信号
S7である。一方、透析液の圧力信号S2は、ほとん
ど変動せず、一定値とみなし得る。 Before starting dialysis, the rotation speed of the blood pump 2 is set according to the physical condition of the patient 13.
Further, the liquid feed pump 9 is also set to a predetermined value. During dialysis, the blood pump 2 and the liquid pump 9 provide a predetermined blood flow rate and dialysate flow rate. At this time, the pressure signal S 1 and the rotational speed signal S 7 have different pulsation cycles depending on the rotational speed (rotational speed) of the blood pump 2, as shown in FIG. In FIG. 5, signals S 1a and S 7a are the pulsating part (period = T 1 ) of the pressure signal S 1 during high-speed rotation and the rotation speed signal S 7
The signals S 1b and S 7b are the pulsating part (period = T 2 > T 1 ) of the pressure signal S 1 during low speed rotation and the rotation signal
It is S7 . On the other hand, the pressure signal S 2 of the dialysate hardly changes and can be regarded as a constant value.
Ａ／Ｄ変換部１８は、演算・制御部１９から送
出されるサンプルレートの異なる信号S5a、又は、
S5b（信号S5a及びS5bについて後述する）によつ
て、信号S1をサンプリングし、デイジタル変換し
た信号S3を出力すると共に、信号S6によつて、信
号S2をサンプリングし、デイジタル変換した信号
S4を出力する。 The A/D conversion unit 18 receives a signal S 5a having a different sample rate sent from the calculation/control unit 19, or
S 5b (signals S 5a and S 5b will be described later) samples the signal S 1 and outputs the digitally converted signal S 3 , and the signal S 6 samples the signal S 2 and outputs the digitally converted signal S 3. converted signal
Output S 4 .
演算・制御部１５は、信号S7a、又はS7b及び内
部発振器に基づくサンプリング信号を発生すると
共に、信号S3及びS4を入力として所定の演算を
し、信号S8を出力する。即ち、前者の動作によつ
て、第５図に示すような信号S5a（信号S7aに対応
する信号）、又は、S5b（信号S7bに対応する信号）
及び一定周期の信号S6（図示省略）が、Ａ／Ｄ変
換部１８に送出される。又、後者の動作によつ
て、時間T1、又はT2を演算時間とした信号S3の
平均値算出演算と、時間T0（一定）を演算時間と
した信号S4の平均値算出演算と、これら２つの平
均値の減算と、その差を測定値とした制御演算と
が行われ、絞り弁５に制御信号S8が送出され、血
液圧力の変動が所定の範囲に制御される。 The calculation/control unit 15 generates a sampling signal based on the signal S 7a or S 7b and an internal oscillator, performs a predetermined calculation using the signals S 3 and S 4 as input, and outputs the signal S 8 . That is, due to the former operation, the signal S 5a (signal corresponding to signal S 7a ) or S 5b (signal corresponding to signal S 7b ) as shown in FIG.
and a constant periodic signal S 6 (not shown) are sent to the A/D converter 18. In addition, by the latter operation, calculation of the average value of the signal S 3 is performed using the time T 1 or T 2 as the calculation time, and calculation of the average value of the signal S 4 is performed using the time T 0 (constant) as the calculation time. Then, a control calculation is performed in which these two average values are subtracted and the difference is used as a measured value, and a control signal S8 is sent to the throttle valve 5, so that fluctuations in blood pressure are controlled within a predetermined range.
上記のように、血液圧力信号は、血液圧力の脈
動周期と一定の関係をもつた信号によつてサンプ
リングされ、デイジタル変換されると共に、前記
脈動周期を演算時間とした平均値算出演算によつ
て平均値信号に変換され、所定の演算部に入力さ
れる。 As mentioned above, the blood pressure signal is sampled by a signal that has a certain relationship with the pulsation period of blood pressure, is digitally converted, and is also subjected to an average value calculation operation using the pulsation period as the calculation time. It is converted into an average value signal and input to a predetermined calculation section.
以上説明したように、前記人工腎臓装置におい
ては、前記血液ポンプの回転によつ血液圧力信号
に脈動が生じ、この血液ポンプの回転数は患者の
体調や年齢に応じて設定されるため前記血液圧力
の変動周期は一定でない。 As explained above, in the artificial kidney device, pulsations occur in the blood pressure signal due to the rotation of the blood pump, and the rotation speed of the blood pump is set according to the patient's physical condition and age. The period of pressure fluctuation is not constant.
これに対し従来装置では前記血液圧力信号のサ
ンプリング周期は固定になつており、変動周期の
短い測定信号に合わせてサンプリング周波数を高
く設定すると、変動周期の長い測定信号の場合に
必要以上にサンプリングを行うことになり無駄と
なり、サンプリング周波数を低く設定すると、変
動周期の短い測定信号の場合に不正確となる。 On the other hand, in conventional devices, the sampling period of the blood pressure signal is fixed, and if the sampling frequency is set high for a measurement signal with a short fluctuation period, sampling will be performed more than necessary for a measurement signal with a long fluctuation period. If the sampling frequency is set low, it will be inaccurate for measurement signals with short fluctuation periods.
本考案によれば、血液圧力信号を、この信号の
脈動周期に応じた周期のサンプリング信号でサン
プリングする為、上記したような欠点は生じな
い。また、前記脈動周期を演算時間にして血液圧
力信号の平均値演算が行われる為、応答性よく血
液圧力の平均値が求められる。 According to the present invention, since the blood pressure signal is sampled with a sampling signal having a period corresponding to the pulsation period of this signal, the above-mentioned drawbacks do not occur. Furthermore, since the average value of the blood pressure signal is calculated using the pulsation period as the calculation time, the average value of the blood pressure can be determined with good responsiveness.
第１図は、従来の人工腎臓装置の構成説明図、
第２図は、血液ポンプの主要部説明図、第３Ａ図
及び第３Ｂ図は、人工腎臓装置の血液系における
血液圧力信号説明図、第４図は、本考案の実施例
装置の構成説明図、第５図は、本考案の装置の動
作説明図である。
１……ダイアライザ、２……血液ポンプ、４…
…血液圧力計、５……絞り弁（オートクレンメ）、
８……透析液貯留槽、９……送液ポンプ、１０…
…透析液圧力計、１７……回転計、１８……Ａ／
Ｄ変換部、１９……演算・制御部。
FIG. 1 is an explanatory diagram of the configuration of a conventional artificial kidney device;
FIG. 2 is an illustration of the main parts of a blood pump, FIGS. 3A and 3B are illustrations of blood pressure signals in the blood system of an artificial kidney device, and FIG. 4 is an illustration of the configuration of an embodiment of the device of the present invention. , FIG. 5 is an explanatory diagram of the operation of the apparatus of the present invention. 1... dialyzer, 2... blood pump, 4...
...Blood pressure gauge, 5... Throttle valve (auto clench),
8... Dialysate storage tank, 9... Liquid feed pump, 10...
...dialysate pressure gauge, 17...tachometer, 18...A/
D conversion section, 19... calculation/control section.
Claims (1)
により採血された血液がダイアライザの膜の一方
側に流され、この膜の他方側に透析液が流され、
血液流路の血液圧力と透析液流路の透析液圧力と
を検出し、夫々の圧力の平均値を求め、これら平
均値の差が所定の値となるように前記血液流路と
透析液流路との間の圧力を制御するようにした人
工腎臓装置において、前記血液ポンプの回転数を
検出する回転計と、後出の演算・制御部から与え
られる一定周波数のサンプリング信号によつて前
記透析液流路の血液圧力信号をサンプリングし、
同じくこの演算・制御部から与えられる、前記回
転計の出力信号の周波数に対応するサンプリング
信号によつて前記透析液流路の透析液圧力信号を
サンプリングし、これらをデイジタル変換する
Ａ／Ｄ変換部と、前記回転計からの出力信号、及
び前記Ａ／Ｄ変換部からの出力信号が与えられ、
前記透析液圧力信号サンプリング用の一定周波数
のサンプリング信号、及び前記血液圧力信号サン
プリング用の前記回転計の出力信号の周波数に対
応したサンプリング信号を前記Ａ／Ｄ変換部に与
え、前記血液圧力の脈動周期を演算時間として前
記血液圧力信号の平均値を求め、前記透析液圧力
信号の平均値との差を演算し、前記血液流路と透
析液流路との間の圧力を制御する信号として出力
する演算・制御部とを具備する人工腎臓装置。 Blood is collected by a blood pump whose rotation speed can be set according to each patient, and the blood is flowed onto one side of the membrane of the dialyzer, and the dialysate is flowed onto the other side of this membrane.
The blood pressure in the blood flow path and the dialysate pressure in the dialysate flow path are detected, the average value of each pressure is determined, and the blood flow path and dialysate flow are adjusted so that the difference between these average values becomes a predetermined value. In an artificial kidney device that controls the pressure between the blood pump and the blood pump, the dialysis is controlled by a tachometer that detects the number of revolutions of the blood pump, and a sampling signal of a constant frequency given from a calculation/control unit to be described later. Sample the blood pressure signal in the fluid flow path,
An A/D converter that samples the dialysate pressure signal in the dialysate flow path using a sampling signal corresponding to the frequency of the output signal of the tachometer, which is also given from the calculation/control unit, and converts the signals into digital data. and an output signal from the tachometer and an output signal from the A/D converter,
A sampling signal of a constant frequency for sampling the dialysate pressure signal and a sampling signal corresponding to the frequency of the output signal of the tachometer for sampling the blood pressure signal are applied to the A/D converter to detect the pulsation of the blood pressure. The average value of the blood pressure signal is determined using a cycle as a calculation time, and the difference between the average value and the dialysate pressure signal is calculated and output as a signal for controlling the pressure between the blood flow path and the dialysate flow path. An artificial kidney device comprising a calculation/control unit that performs the following operations.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP13747681U JPS5843450U (en) | 1981-09-16 | 1981-09-16 | artificial kidney device |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP13747681U JPS5843450U (en) | 1981-09-16 | 1981-09-16 | artificial kidney device |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| JPS5843450U JPS5843450U (en) | 1983-03-23 |
| JPS639320Y2 true JPS639320Y2 (en) | 1988-03-18 |
Family
ID=29930751
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| JP13747681U Granted JPS5843450U (en) | 1981-09-16 | 1981-09-16 | artificial kidney device |
Country Status (1)
| Country | Link |
|---|---|
| JP (1) | JPS5843450U (en) |
Families Citing this family (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPS59181162A (en) * | 1983-03-31 | 1984-10-15 | 日本メディカルエンジニアリング株式会社 | Control of dialytic apparatus and automatic dialytic apparatus |
| JPS6133642A (en) * | 1984-07-27 | 1986-02-17 | 新技術事業団 | Blood pressure wave form signal processing method and apparatus for auxilary circulation |
| JP2005233681A (en) * | 2004-02-17 | 2005-09-02 | Jms Co Ltd | Pressure measuring system and pressure measurement method |
| JP5026558B2 (en) * | 2010-05-24 | 2012-09-12 | 株式会社ジェイ・エム・エス | Hemodialysis machine |
Citations (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPS57190547A (en) * | 1981-05-21 | 1982-11-24 | Terumo Corp | Monitor apparatus for blood recirculating circuit in external body |
-
1981
- 1981-09-16 JP JP13747681U patent/JPS5843450U/en active Granted
Patent Citations (1)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| JPS57190547A (en) * | 1981-05-21 | 1982-11-24 | Terumo Corp | Monitor apparatus for blood recirculating circuit in external body |
Also Published As
| Publication number | Publication date |
|---|---|
| JPS5843450U (en) | 1983-03-23 |
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