JPH01131669A - Blood dialyzer - Google Patents
Blood dialyzerInfo
- Publication number
- JPH01131669A JPH01131669A JP62291629A JP29162987A JPH01131669A JP H01131669 A JPH01131669 A JP H01131669A JP 62291629 A JP62291629 A JP 62291629A JP 29162987 A JP29162987 A JP 29162987A JP H01131669 A JPH01131669 A JP H01131669A
- Authority
- JP
- Japan
- Prior art keywords
- amount
- water
- pressure difference
- transmembrane pressure
- water removal
- 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.)
- Pending
Links
- 239000008280 blood Substances 0.000 title abstract description 9
- 210000004369 blood Anatomy 0.000 title abstract description 9
- XLYOFNOQVPJJNP-UHFFFAOYSA-N water Substances O XLYOFNOQVPJJNP-UHFFFAOYSA-N 0.000 claims abstract description 95
- 238000001631 haemodialysis Methods 0.000 claims description 10
- 230000000322 hemodialysis Effects 0.000 claims description 10
- 238000000502 dialysis Methods 0.000 abstract description 20
- 239000012528 membrane Substances 0.000 abstract description 3
- 238000006243 chemical reaction Methods 0.000 description 4
- 238000001514 detection method Methods 0.000 description 3
- 238000000034 method Methods 0.000 description 3
- 230000017531 blood circulation Effects 0.000 description 2
- 238000007485 conventional hemodialysis Methods 0.000 description 2
- 238000010586 diagram Methods 0.000 description 2
- 239000002699 waste material Substances 0.000 description 2
- HTTJABKRGRZYRN-UHFFFAOYSA-N Heparin Chemical compound OC1C(NC(=O)C)C(O)OC(COS(O)(=O)=O)C1OC1C(OS(O)(=O)=O)C(O)C(OC2C(C(OS(O)(=O)=O)C(OC3C(C(O)C(O)C(O3)C(O)=O)OS(O)(=O)=O)C(CO)O2)NS(O)(=O)=O)C(C(O)=O)O1 HTTJABKRGRZYRN-UHFFFAOYSA-N 0.000 description 1
- 230000002159 abnormal effect Effects 0.000 description 1
- 230000023555 blood coagulation Effects 0.000 description 1
- 230000007423 decrease Effects 0.000 description 1
- 238000007872 degassing Methods 0.000 description 1
- 239000000385 dialysis solution Substances 0.000 description 1
- 230000000694 effects Effects 0.000 description 1
- 229960002897 heparin Drugs 0.000 description 1
- 229920000669 heparin Polymers 0.000 description 1
- 239000007924 injection Substances 0.000 description 1
- 238000002347 injection Methods 0.000 description 1
- 239000007788 liquid Substances 0.000 description 1
- 238000005259 measurement Methods 0.000 description 1
- 230000001105 regulatory effect Effects 0.000 description 1
- 230000035939 shock Effects 0.000 description 1
- 239000011550 stock solution Substances 0.000 description 1
- 238000000108 ultra-filtration Methods 0.000 description 1
- 210000002700 urine Anatomy 0.000 description 1
Landscapes
- External Artificial Organs (AREA)
Abstract
Description
【発明の詳細な説明】
(産業上の利用分野)
本発明は血液透析の際に、除水速度および除水量を自動
的に調整する除水量制御手段を備えた血液透析装置に関
するものである。 。DETAILED DESCRIPTION OF THE INVENTION (Industrial Application Field) The present invention relates to a hemodialysis apparatus equipped with water removal amount control means that automatically adjusts the water removal rate and amount of water removed during hemodialysis. .
(従来の技術と問題点)
血液透析において患者の体重を減少させるための除水量
の調節は極めて正確に行なわなければならない。なぜな
ら、急激な除水を行なうと患者にショックを与えること
になシ、また、総除水量も患者の健康状態を充分に加味
した量が設定されるからである。(Prior Art and Problems) In hemodialysis, the amount of water removed must be extremely accurately adjusted in order to reduce the patient's weight. This is because rapid water removal will not cause shock to the patient, and the total amount of water removed is set at an amount that fully takes into account the health condition of the patient.
一般の血液透析においてUF(限外ろ過)による総除水
量は1回の透析で2ないし31であるのに対し、その透
析液の量は1501である。したがって、上記除水量は
透析液の4に対して工ないし24にしか相当せず、この
除水量を実用範囲(±5 Q cc )で制御するため
には、透析液の量を実に0.03ないし0.04%の誤
差範囲内に収めなければならない。In general hemodialysis, the total amount of water removed by UF (ultrafiltration) is 2 to 31 in one dialysis, whereas the amount of dialysate is 1,501. Therefore, the amount of water removed corresponds to only 24 to 4 of the dialysate, and in order to control the amount of water removed within a practical range (±5 Q cc ), the amount of dialysate must be adjusted to 0.03 It must be within an error range of 0.04% to 0.04%.
ところが、従来の血液透析は、透析前に患者の体重を測
り、その体重を何に?落とすかを設定した恥
のち、前回透析のデータを基に・で透析液の流量と透析
時間を設定するというもので、透析液の流量は一定にし
たままの状態であった。したがって、上記の方法は、最
終的な除水量が透析後の患者の体重を測って透析前の体
重との差を計算すること初
により・めて分かるという、極めて原始的なものであり
、除水量の正確な調整が困難である。However, in conventional hemodialysis, the patient's weight is measured before dialysis, and what is the weight? After setting the dialysis fluid flow rate, the dialysate flow rate and dialysis time were set based on the data from the previous dialysis, and the dialysate flow rate remained constant. Therefore, the above method is an extremely primitive method in which the final amount of water removed can only be determined by measuring the patient's weight after dialysis and calculating the difference between the patient's weight and the weight before dialysis. It is difficult to accurately adjust the amount of water.
また、上記の調整方法より一歩進んだものとして5例え
ば特開昭54−27296号公報の発明の装置がある。Furthermore, there is an apparatus which is one step more advanced than the above-mentioned adjustment method, for example, as disclosed in Japanese Patent Application Laid-Open No. 54-27296.
この装置は、透析液の排出量をシリンダで逐次計測し、
その排出量の変化に基づいて透析液の流量を調節する構
成となっている。This device measures the amount of dialysate discharged sequentially using a cylinder.
The configuration is such that the flow rate of the dialysate is adjusted based on changes in the discharge amount.
ところが、上記の調整装置においても除水量の計測はあ
まり正確とはいえず、除水連間の変動が激しくなる危険
性があり、最終的な除水量も正確なものが期待できない
。また、流路が詰まるなどの不測の事故に対しても何ら
対応策がなされていない。However, even with the above-mentioned adjustment device, the measurement of the amount of water removed is not very accurate, and there is a risk that fluctuations between the water removal stations will be large, and the final amount of water removed cannot be expected to be accurate. Furthermore, no countermeasures have been taken against unforeseen accidents such as clogging of the flow path.
また、従来の血液透析においては、患者1人に対して多
くの熟練したスタッフが付き添うことが必要であり、そ
の経費および人員確保の面で多くの問題が残されていた
。Furthermore, in conventional hemodialysis, it is necessary for a large number of skilled staff to attend to each patient, and many problems remain in terms of costs and securing personnel.
さらに、除水速度は時間的に一定にすれば良いというも
のではなく、患者1人1人に合った除水速度の時間的変
化特性があるので、その特性に忠実に、しかも、正確に
透析を行なえる調節装置の開発が望まれている。Furthermore, it is not enough to keep the water removal rate constant over time, but since there is a time-varying characteristic of the water removal rate that suits each patient, it is possible to perform dialysis while faithfully following these characteristics. It is desired to develop an adjustment device that can perform this.
したがって本発明の目的は除水量を正確、かつ自動的に
計測制御し、安全に血液透析を行うことのできる除水量
制御手段を備えた血液透析後置を提供することにある。Therefore, an object of the present invention is to provide a hemodialysis post-dialysis device equipped with water removal amount control means that can accurately and automatically measure and control the amount of water removed and safely perform hemodialysis.
(問題点を解決するための手段〉
上記目的を達成するため、この発明は第1図に示すよう
に透析液サプライヤ1から透析液流入路2を介して血液
透析器りに導入される透析液の流量を計測する第1の流
量計3と、透析液流出路4を介して血液透析器2から導
出される血液中の老廃物を含む透析液の流量を計測する
第2の流量計6と、透析液流出路4と血液循環路9に設
けられて血液透析器の膜間圧力差を検出する2つの圧力
センサ7.8と、患者Mからの総除水量を設定するれ延
除水量と前回算出された延除水量との比較から瞬時除水
量を算出する瞬時除水量演算手段11と、上記瞬時除水
量を総除水量に換算して、除水量設定手段10で設定さ
れた総除水量との比較から総除水量の差を演算する除水
量算出手段12と、上記総除水量の差を膜間圧力差に換
算し、該換′抹さ咋た膜間圧力差を前回算出された膜間
圧力差の設定値に加算して膜間圧力差の設定値を変(す
る膜間圧力差設定手段13と、上記膜間圧力差設定手段
13で設定された膜間圧力差と圧力上ンf 7゜8で検
出された膜間圧力差を比較しながら両者の偏差値が零と
なるまでポンプの回転数を制御する膜間圧力差制御手段
15とを備えた構成とし、上記除水量設定手段10の設
定値に合致した透析がなされるように除水速度を制御し
ている。(Means for Solving the Problems) In order to achieve the above object, the present invention provides dialysate that is introduced into a hemodialyzer from a dialysate supplier 1 through a dialysate inflow path 2, as shown in FIG. a first flowmeter 3 that measures the flow rate of the dialysate, and a second flowmeter 6 that measures the flow rate of the dialysate containing waste products in the blood, which is led out from the hemodialyzer 2 via the dialysate outflow path 4. , two pressure sensors 7.8 provided in the dialysate outflow path 4 and the blood circulation path 9 to detect the transmembrane pressure difference of the hemodialyzer, and a total amount of water removed from the patient M. The instantaneous water removal amount calculating means 11 calculates the instantaneous water removal amount from comparison with the total water removal amount calculated last time, and the total water removal amount set by the water removal amount setting means 10 converts the instantaneous water removal amount into the total water removal amount. A water removal amount calculating means 12 calculates the difference in the total amount of water removed from a comparison with the amount of water removed; A transmembrane pressure difference setting means 13 that changes the set value of the transmembrane pressure difference by adding it to the set value of the transmembrane pressure difference, and a transmembrane pressure difference set by the transmembrane pressure difference setting means 13 and the pressure and a transmembrane pressure difference control means 15 that controls the rotation speed of the pump while comparing the transmembrane pressure difference detected at the pump f7°8 until the deviation value between the two becomes zero, and the above-mentioned amount of water removed is The water removal rate is controlled so that dialysis is performed in accordance with the setting value of the setting means 10.
(作 用)
この発明では一定時間毎に計測された瞬時除水量を一定
時間後(透析終了予定時間)の除水量にまず換算して、
この換算値と予じめ設定された除水量との差を算出し、
次いでこの除水量の差を膜間圧力差に換算して前回算出
した膜間圧力差の設定値に加算し、この加算された値を
次回の膜間圧力差の設定値とすることによシ、血液透析
中に変化する患者の状態に適応した正確な除水量を得る
ことができ、かつ不測の事故に対しても敏速に対応する
ことができる。(Function) In this invention, the instantaneous amount of water removed measured at regular intervals is first converted into the amount of water removed after a certain period of time (scheduled end time of dialysis).
Calculate the difference between this converted value and the preset water removal amount,
Next, this difference in the amount of water removed is converted into a transmembrane pressure difference and added to the previously calculated transmembrane pressure difference set value, and this added value is set as the next transmembrane pressure difference set value. It is possible to obtain an accurate amount of water removal that is adapted to the patient's changing condition during hemodialysis, and it is also possible to quickly respond to unexpected accidents.
(実施例)
第2図はこの発明の一実施例にかかる血液透析装置を示
す構成図である。第2図において、サブライヤ20では
水と透析原液とを混ぜて適度な透析液が作られる。この
透析液は加圧ポンプ21によって昇圧されて矢印F1方
向に流れ、ヒータ22で透析に最適な温度に加熱され、
脱気ポンプ23で脱気され、さらに流を調節バルブ24
で一定の流量に調整されたのち、オーバルメータ(第1
の流量計)3を通って血液透析器りに流入する。−方血
液透析器の内部で老廃物を吸収した透析液はこの血液透
析器○を流出し、オーバルメータ(第2の流量計)6を
通ってポンプ16で排出される。(Example) FIG. 2 is a configuration diagram showing a hemodialysis apparatus according to an example of the present invention. In FIG. 2, a sublayer 20 mixes water and a dialysis stock solution to produce a suitable dialysate. This dialysate is pressurized by the pressurizing pump 21 and flows in the direction of arrow F1, and is heated to the optimum temperature for dialysis by the heater 22.
It is degassed by the degassing pump 23, and the flow is further controlled by the regulating valve 24.
After the flow rate is adjusted to a constant level, the oval meter (first
(flow meter) 3 into the hemodialyzer. - The dialysate that has absorbed waste products inside the hemodialyzer flows out of the hemodialyzer ○, passes through an oval meter (second flow meter) 6, and is discharged by a pump 16.
一方、人体Mから取り出された血液は血液ポンプ25に
よって矢印F2方向に流速が加えられ、血液透析器に送
り込まれる。血液透析器で透析された血液は、空気デテ
クタ26を通って人体Mに戻される。27はヘパリンポ
ンプで、血液中に尿成分を少量だけ混入させ、血液透析
中の血液凝固を防止する。28はビュロースイッチで血
液を採取する注射針が詰まったりしたときに直ちに血液
の流れをしゃ断する。On the other hand, the blood taken out from the human body M is applied a flow velocity in the direction of arrow F2 by the blood pump 25, and is sent to the hemodialyzer. The blood dialyzed by the hemodialyzer is returned to the human body M through the air detector 26. 27 is a heparin pump that mixes a small amount of urine components into the blood to prevent blood coagulation during hemodialysis. Reference numeral 28 is a bureau switch that immediately cuts off the flow of blood when the injection needle used to collect blood becomes clogged.
7.8は透析液流出路及び血液流路に設けられた圧力セ
ンナであり、この2つの圧力センサにより膜間圧力差が
算出できる。7.8 is a pressure sensor provided in the dialysate outflow path and the blood flow path, and the transmembrane pressure difference can be calculated by these two pressure sensors.
上記オーバルメータ3,6で透析液の流入量と流出量を
示すパルス数が周期的に検出され、そのデータは瞬時除
水量演算手段11ヘパルス信号として送られる。この瞬
時除水量演算手段11では第4図に示すように上記オー
バルメータ3によって検出された透析液の流入量を表わ
すパルス数[C1n(tn)]とオーバルメータ6によ
って検出された透析液の流出量を表わすパルス数[Co
ut(tn) )からその差[:CD(tn)=Con
t(tn)−C1n(tn):lを演算して、除水量制
御手段12に送出している。除水量制御手段12は上記
瞬時除水量を表わすパルス!、: [CD(tn)’]
を透析終了時における除水fi [UFR(tn)]に
換算する手段31と換算された除水量と予じめ設定され
た除水量已疋R]との差を算出する手段32で構成され
ている。上記除水量換算手段31では瞬時除水量演算手
段11で周期的に演算される瞬時除水量を表わすパルス
数の増加分1:cD(tn)−Co(tn−+ ) )
から瞬時除水速度をまず算出し、次いで得られた除水速
度から透析終了後の除水量に撲ユする。例えば第3図に
示すようにオーバルメータの一方の回転子31の対称位
置にそれぞれ磁石32を埋設し、この磁石をオーバルメ
ータの筐体330表面に取着した磁気感応センサ(図示
せず)で検出する場合には、回転子31が一回転すると
2個のパルスが発信される。この回転子31が一回転に
つ1!1dの液体を流出させるとするとオーバルメータ
のレートは0.5d/パルスとなる。したがって例えば
1分間毎に瞬時除水量を演算すると瞬時除水量の増加、
すなわち1分間に30パルスの増加があれば瞬時除水速
度は30X0.5X60=9001!J膚として算出さ
れ、次いでこの値が透析終了後の除水量に換算される。The oval meters 3 and 6 periodically detect the number of pulses indicating the inflow and outflow of the dialysate, and the data is sent as a pulse signal to the instantaneous water removal amount calculation means 11. As shown in FIG. 4, this instantaneous water removal amount calculation means 11 calculates the number of pulses [C1n(tn)] representing the inflow of dialysate detected by the oval meter 3 and the outflow of dialysate detected by the oval meter 6. The number of pulses representing the amount [Co
ut(tn) ) to the difference [:CD(tn)=Con
t(tn)-C1n(tn):l is calculated and sent to the water removal amount control means 12. The water removal amount control means 12 generates a pulse representing the instantaneous water removal amount! , : [CD(tn)']
The system comprises a means 31 for converting the amount of water removed to a water removal amount [UFR(tn)] at the end of dialysis, and a means 32 for calculating the difference between the converted amount of water removal and a preset amount of water removal [UFR(tn)]. There is. In the water removal amount conversion means 31, the increase in the number of pulses representing the instantaneous water removal amount calculated periodically by the instantaneous water removal amount calculation means 11 is 1:cD(tn)-Co(tn-+))
The instantaneous water removal rate is first calculated, and then the amount of water removed after dialysis is determined from the obtained water removal rate. For example, as shown in FIG. 3, magnets 32 are embedded in symmetrical positions of one rotor 31 of an oval meter, and the magnets are attached to the surface of a housing 330 of the oval meter to create a magnetically sensitive sensor (not shown). In the case of detection, two pulses are transmitted when the rotor 31 rotates once. Assuming that this rotor 31 discharges 1!1 d of liquid per revolution, the oval meter rate will be 0.5 d/pulse. Therefore, for example, if the instantaneous water removal amount is calculated every minute, the instantaneous water removal amount will increase,
In other words, if there is an increase of 30 pulses per minute, the instantaneous water removal rate is 30X0.5X60=9001! This value is then converted to the amount of water removed after dialysis.
透析時間を4時間と設定すれば透析終了後の除水量(U
FR(tn)〕は3.600dとなる。上記除水量換算
手段31からの信号〔UF R(tn) )は設定除水
量との差算出手段32に発信され除水量設定手段10で
予じめ設定された除水量(UFR(!l))と比較され
て両者の差(e(tn)=UFR(s) −UFR(t
n))が算出される。If the dialysis time is set to 4 hours, the amount of water removed after dialysis (U
FR(tn)] is 3.600d. The signal [UF R (tn)) from the water removal amount conversion means 31 is sent to the difference calculation means 32 from the set water removal amount, and the water removal amount (UFR (!l)) set in advance by the water removal amount setting means 10 is sent. The difference between the two (e(tn) = UFR(s) - UFR(t
n)) is calculated.
除水量制御手段12からの信号(e(tn)Eは次いで
膜間圧力差設定手段13に発信される。該膜間圧力差設
定手段13は上記除水量制御手段12から発信された信
号(e(tn))を膜間圧力差(TMP)に換算する膜
間圧力差換算手段33と換算された膜間圧力差を前回算
出された膜間圧力差の設定値に加算して膜間圧力差の設
定値を変更する膜間圧力差設定値算出手段34で構成さ
れている。上記膜間圧力差換算手段33では、除水量制
御手段12から発信された信号(e(tn))と、前回
得られ免除水量の差信号(e(tn−1))からその差
〔Δe (tn) =e(tn) −e(tn−1):
lを算出し、次いで前回得られた除水量の差と前々回得
られた除水量の差〔ΔΔe(tn)=Δa(tn)−Δ
e(tn−1))を算出し、上記算出された値と予じめ
与えられた比例定数(Kp)、積分定数(K■)、微分
定数(KD)を用いテKp−e(tn)+Kl −Δe
(tn) +KD −品e (tn)なる比例積分微
分演算がなされ、除水量(e (tn))が膜間圧力差
(TMP(6(tn)) )に換算される。次いで上記
膜間圧力差(TMP (e(tn) ) )は膜間圧力
差設定値算出手段34で前回算出された膜間圧力差の設
定値(TMP(tn−1))に加算される。そしてその
加算された膜間圧力差(TMP (tn)) −[TM
P (tn−1)]+(TMP(e(tn)月が次回の
膜間圧力差の設定値とされる。The signal (e(tn)E) from the water removal amount control means 12 is then transmitted to the transmembrane pressure difference setting means 13. The transmembrane pressure difference conversion means 33 converts (tn)) into a transmembrane pressure difference (TMP), and the transmembrane pressure difference is added to the set value of the transmembrane pressure difference calculated previously to calculate the transmembrane pressure difference. The transmembrane pressure difference setting value calculating means 34 changes the set value of the transmembrane pressure difference. From the difference signal (e(tn-1)) of the exempt water amount obtained, the difference [Δe (tn) = e(tn) - e(tn-1):
1 is calculated, and then the difference between the amount of water removed obtained last time and the amount of water removed obtained the day before last [ΔΔe (tn) = Δa (tn) - Δ
e(tn-1)), and using the above calculated value and the pre-given proportionality constant (Kp), integral constant (K■), and differential constant (KD), calculate teKp-e(tn). +Kl −Δe
(tn) +KD - product e (tn) A proportional-integral-differential calculation is performed, and the amount of water removed (e (tn)) is converted to a transmembrane pressure difference (TMP (6 (tn))). Next, the transmembrane pressure difference (TMP (e(tn) )) is added to the previously calculated transmembrane pressure difference set value (TMP (tn-1)) by the transmembrane pressure difference set value calculation means 34 . Then, the added transmembrane pressure difference (TMP (tn)) − [TM
P (tn-1)]+(TMP(e(tn)) The month is set as the next transmembrane pressure difference setting value.
上記膜間圧力差設定値換算手段34に初期膜間圧力差設
定手段(図示せず)からの設定値を入力するようにして
もよい。この場合には1回目の膜間圧力差設定時に初期
の設定値に膜間圧力差の換算値(TMP (e (tl
) ) )が加算される。このように膜間圧力差の初期
設定値を入力するようにしておくと1〜2回目の膜間圧
力差の設定値として異常な膜間圧力差が設定されること
を防止できる。A set value from an initial transmembrane pressure difference setting means (not shown) may be input to the transmembrane pressure difference set value conversion means 34. In this case, when setting the transmembrane pressure difference for the first time, the converted value of the transmembrane pressure difference (TMP (e (tl
) ) ) is added. By inputting the initial setting value of the transmembrane pressure difference in this way, it is possible to prevent an abnormal transmembrane pressure difference from being set as the first or second transmembrane pressure difference setting value.
このように膜間圧力差の設定値は、周期的に瞬時除水量
が演算される毎に変更されることになる。In this way, the set value of the transmembrane pressure difference is changed every time the instantaneous water removal amount is calculated periodically.
上記膜間圧力差設定手段13から発信された信号(T
M P (tn))は、次にD/A変換器35でアナロ
ブ信号に変換されて膜間圧力差制御手段15に送出され
る。この膜間圧力差制御手段15の回転数指令信号生成
手段36では、上記膜間圧力差の設定値と2つのセンサ
7.8より検出される信号から膜間圧力差を算出する膜
間圧力差算出手段37からの検出値とを比較して両者の
差分から比例積分微分演算を行ない回転数指令信号を生
成する。A signal (T
M P (tn)) is then converted into an analog signal by the D/A converter 35 and sent to the transmembrane pressure difference control means 15 . The rotation speed command signal generating means 36 of the transmembrane pressure difference control means 15 calculates the transmembrane pressure difference from the set value of the transmembrane pressure difference and the signals detected by the two sensors 7.8. The detected value from the calculation means 37 is compared and a proportional integral differential calculation is performed based on the difference between the two to generate a rotation speed command signal.
この回転数指令信号はポンプ16のドライバ部に印加さ
れる。つまり、回転数指令信号電圧〉回転数検出信号電
圧の状態であれば、ドライバ部からモータへの電力供給
が増大してモータの回転数、換言すればポンプ5の回転
数は増大し、逆に回転数指令信号電圧〈回転数検出信号
電圧の状態であれば、モータの回転数は減少するもので
、上記ポンプ5の回転数は上記回転数指令信号に追従す
るように自動制御される。したがって膜間圧力差を常時
膜間圧力差設定手段13で設定された値に追従させるこ
とができ、除水量を正確にコントロールできる。This rotational speed command signal is applied to the driver section of the pump 16. In other words, if the rotation speed command signal voltage is greater than the rotation speed detection signal voltage, the power supply from the driver section to the motor increases and the rotation speed of the motor, in other words, the rotation speed of the pump 5 increases; If the rotation speed command signal voltage is the same as the rotation speed detection signal voltage, the rotation speed of the motor decreases, and the rotation speed of the pump 5 is automatically controlled to follow the rotation speed command signal. Therefore, the transmembrane pressure difference can always be made to follow the value set by the transmembrane pressure difference setting means 13, and the amount of water removed can be accurately controlled.
(発明の効果)
以上のように本発明装置は除水量設定手段の設定値に合
致した透析がなされるように除水速度を制御するため患
者に不快感を与えることなく正砲な除水量を得ることが
でき、不測の事故に対する処置を敏速に行うことができ
るとともに、作業が簡単で初心者も容易に使用できる。(Effects of the Invention) As described above, the device of the present invention controls the water removal rate so that dialysis is performed in accordance with the setting value of the water removal amount setting means, so that a proper amount of water removal can be performed without causing discomfort to the patient. In addition to being able to quickly take measures against unexpected accidents, the work is simple and even beginners can easily use it.
第1図及び第2図は本発明の構成を示す系統図であシ、
第3図は流量計の構造を示す断面図であり、第4図は本
発明の詳細な説明するためのグラフである。
3.6・・・・・・・・・・・・第1及び第2の流量計
7.8・・・・・・・・・・・・圧力センサ10 ・・
・・・・・・・・・・除水量設定手段11 ・・・・・
・・・・・・・瞬時除水全演算手段12 ・・・・・・
・・・・・・除水量算出手段13 ・・・・・・・・・
・・・膜間圧力差設定手段15 ・・・・・・・・・・
・・膜間圧力差制御手段特許出願人 株式会社 り
ラ し1 and 2 are system diagrams showing the configuration of the present invention,
FIG. 3 is a sectional view showing the structure of the flowmeter, and FIG. 4 is a graph for explaining the present invention in detail. 3.6......First and second flowmeters 7.8......Pressure sensor 10...
......Water removal amount setting means 11...
・・・・・・ Instant water removal total calculation means 12 ・・・・・・
...Water removal amount calculation means 13 ......
...Membrane pressure difference setting means 15 ......
...Transmembrane pressure difference control means patent applicant Ri Co., Ltd.
La Shi
Claims (1)
る透析液の流量を計測する流量計と、透析液流出路に設
けられたポンプと、血液透析器の膜間圧力差を検出する
圧力センサと、総除水量を設定する除水量設定手段と、
上記2つの流量計の一定時間毎の計測値から延除水量を
算出し、該算出された延除水量と前回算出された延除水
量との比較から瞬時除水量を算出する瞬時除水量演算手
段と、上記瞬時除水量を総除水量に換算して、除水量設
定手段で設定された総除水量との比較から総除水量の差
を演算する除水量算出手段と、上記総除水量の差を膜間
圧力差に換算し、該換算された膜間圧力差を前回算出さ
れた膜間圧力差の設定値に加算して膜間圧力差の設定値
を変更する膜間圧力差設定手段と、上記膜間圧力差設定
手段で設定された膜間圧力差と圧力センサで検出された
膜間圧力差を比較しながら両者の偏差値が零となるまで
ポンプの回転数を制御する膜間圧力差制御手段とを備え
たことを特徴とする血液透析装置。A flow meter that measures the flow rate of dialysate flowing through the dialysate inflow path and dialysate outflow path to the hemodialyzer, a pump installed in the dialysate outflow path, and a pressure that detects the transmembrane pressure difference between the hemodialyzer. a sensor, a water removal amount setting means for setting a total water removal amount;
An instantaneous amount of water removal calculation means that calculates the total amount of water removed from the measured values of the two flowmeters at regular intervals, and calculates the instantaneous amount of water removed from a comparison between the calculated amount of water removed and the previously calculated amount of water removed. and a water removal amount calculating means for converting the instantaneous water removal amount into a total water removal amount and calculating a difference in the total water removal amount from a comparison with the total water removal amount set by the water removal amount setting means, and a difference in the total water removal amount. transmembrane pressure difference setting means for converting the transmembrane pressure difference into a transmembrane pressure difference and adding the converted transmembrane pressure difference to the previously calculated transmembrane pressure difference set value to change the transmembrane pressure difference set value; The transmembrane pressure is controlled by comparing the transmembrane pressure difference set by the transmembrane pressure difference setting means with the transmembrane pressure difference detected by the pressure sensor and controlling the rotation speed of the pump until the deviation value between the two becomes zero. A hemodialysis apparatus comprising differential control means.
Priority Applications (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
JP62291629A JPH01131669A (en) | 1987-11-17 | 1987-11-17 | Blood dialyzer |
Applications Claiming Priority (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
JP62291629A JPH01131669A (en) | 1987-11-17 | 1987-11-17 | Blood dialyzer |
Publications (1)
Publication Number | Publication Date |
---|---|
JPH01131669A true JPH01131669A (en) | 1989-05-24 |
Family
ID=17771431
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
JP62291629A Pending JPH01131669A (en) | 1987-11-17 | 1987-11-17 | Blood dialyzer |
Country Status (1)
Country | Link |
---|---|
JP (1) | JPH01131669A (en) |
Cited By (2)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
JP2008073563A (en) * | 1998-07-31 | 2008-04-03 | Baxter Internatl Inc | Apparatus and system for performing controlled ultrafiltration during hemodialysis |
US10682451B2 (en) | 2015-04-22 | 2020-06-16 | Nikkiso Co., Ltd. | Calibration method for flowmeters in blood dialysis system |
-
1987
- 1987-11-17 JP JP62291629A patent/JPH01131669A/en active Pending
Cited By (2)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
JP2008073563A (en) * | 1998-07-31 | 2008-04-03 | Baxter Internatl Inc | Apparatus and system for performing controlled ultrafiltration during hemodialysis |
US10682451B2 (en) | 2015-04-22 | 2020-06-16 | Nikkiso Co., Ltd. | Calibration method for flowmeters in blood dialysis system |
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