JPS58155864A - Blood purifying apparatus - Google Patents

Abstract

(57) [Summary] This bulletin contains application data before electronic filing, so abstract data is not recorded.

Description

DETAILED DESCRIPTION OF THE INVENTION The present invention relates to a blood purification device that purifies blood by dialysis or filtration through a semipermeable membrane, and particularly to a blood purification device that automatically adjusts blood circulation and fluid volume changes in a patient's body during blood purification. It is about improvement.

In recent years, in the treatment of patients whose ability to remove waste products from the blood has been impaired due to renal dysfunction, such as renal failure, blood is taken out of the body, purified by dialysis or filtration through a semipermeable membrane, and then returned to the body. A blood purification device is used to return the blood to blood.

As is well known, in this type of apparatus, excess water in waste products is removed by ultrafiltration, but the water removal rate at this time must be at an appropriate value. In other words, rapid or excessive water removal can cause a sudden decrease in the amount of fluid circulating in the patient's body, which can lead to complications such as decreased arterial pressure or swelling, whereas slow water removal can cause It is known that blood purification takes a long time, and if sufficient water cannot be removed, it may cause high internal pressure or heart failure.

Therefore, in conventional devices, in order to maintain the water removal rate appropriately, for example, in hemodialysis (hemodialysis), the ultrafiltration rate is kept constant during the dialysis time, or the water removal rate is set in advance at the start of dialysis. ! The ultrafiltration rate is controlled according to the program.

However, in recent years, it has become clear that controlling the ultrafiltration rate alone cannot solve various problems that occur during blood purification. In other words, these problems are mainly caused by an excessive decrease in the amount of blood circulating in the body, but this fluctuation in blood volume in the body is not only caused by the ultrafiltration rate mentioned above, but also by the amount of water in the blood passing through the capillaries. , water in solutes or interstitial fluids, and the movement speed of solutes. Therefore, conventional control that focuses only on ultrafiltration rate and ultrafiltration rate is an effective way to properly control the amount of blood circulating in the body. It has become clear that this is difficult.

As an appropriate control method during other conventional blood purification,
It has been proposed to measure the electrical resistance (impedance) of blood and use this to perform control to prevent excessive removal of water from the body during fluid purification.
Extracorporeal circulation iJ during hemodialysis! The electrical resistance changes of the blood are measured on the arterial side of the circuit, or between the arterial and venous sides, and the operating speed of the hemodialyzer is controlled based on these resistance changes, or serum preparations are introduced into the internal fluid circulation path. The injection is controlled.

However, even in this conventional device, the electrical resistivity of blood is determined not only by the concentration of chemical elements or the amount of water;
Electrical resistivity changes greatly depending on other factors such as temperature of the blood, countercurrent velocity, and in particular the orientation of red blood cells caused by blood flow, and the phenomenon of convergence. It is difficult to determine changes in the amount of water in the body and to control the amount of blood circulating in the body appropriately based on this information.

*In detail, conventional blood electrical resistivity measurements are performed by placing electrodes spaced apart in the direction of blood flow and passing a constant current through the electrodes during this time. For example, the measurement frequency 19 KHIg
, blood hetocrit 36- is 8 Mar
At ats 106 s, a decrease of about 12 − compared to rest can be seen.

Furthermore, in conventional control devices, the purification rate is always adjusted to the patient's condition.
It does not automatically control according to IK, but simply controls each ItOI.
II Constant Monitoring Output For example, when the change in O electrical resistivity in the liquid exceeds a predetermined critical value, the purification speed and other parameters are temporarily controlled only at 9 o'clock. Similarly, there is a fundamental problem in that the purification is carried out under only nine predetermined purification conditions, making it impossible to perform overall and continuous appropriate water removal control.

In addition, in order to properly purify blood in 1N liquid filtration (hemofiltration), which is another method of blood purification, when removing a large amount of water from the 161 liquid along with unnecessary substances, this It is necessary to replenish the replacement fluid in an amount equal to or slightly smaller than the amount of water removed to prevent a sudden decrease in the amount of blood circulating in the body.

For this reason, in white liquor filtration devices, it is considered that the weight difference or volume difference between the two liquids is controlled to a predetermined value in order to balance the amount of filtrate and the amount of replenisher. With this method, the equipment becomes complicated and large, and as mentioned above,
Since the amount of blood circulating in a patient's body is not determined solely by K (the difference between the amount of water-removed ilC filtrate and the amount of replacement fluid), it has been impossible to appropriately control the amount of blood circulating in the patient's body.

The present invention was developed in view of the above-mentioned conventional problems, and its purpose is to efficiently purify blood by extracting blood outside the patient's body while maintaining the amount of fluid circulating in the patient's body at an appropriate value. It is an object of the present invention to provide a blood purification device that can stably perform good water removal.

In order to achieve the above object, the immersion device of the present invention has the following features:
The amount of circulating blood in the body is continuously measured during internal fluid purification, for example, from the hematocrit level, which is inversely proportional to the amount of circulating own fluid.
This measured value or the calculated value can be set based on various records of the patient! Automatically controls the water removal rate or replenisher injection rate to match the program.

Furthermore, in the present invention, in addition to measuring the amount of fluid circulating in the body, the amount of water removed from the patient is continuously measured, and the ζO water removal rate is controlled according to a predetermined 7'0. It is characterized by its optimal water removal effect even for patients who require management.

Embodiments of the present invention will be explained in detail below based on the drawings.

FIG. 1 shows the basic configuration of a first embodiment in which the present invention is used for hemodialysis. It includes a dialysate system 1 for supplying fluid and a control system 14 for driving and controlling the vacuum inlet 128 in accordance with the hematocrit value detected in the moat circulation system IO.

A white liquor circulation system 10 transports the patient's blood from an inlet tube 16 to a dialyzer 1.
8, and after performing blood dialysis and ultrafiltration in cooperation with the dialysate system 12, the purified fluid is returned to the patient's body through the return tube 20, and the blood circulation at this time is as follows: This is done by circulation I-in 122.

In the present invention, in order to provide an optimal water removal effect to the general dialysis machine described above, a hematocrit constant device 24 is provided in the blood circulation system 10, and the electrical resistivity of the blood is continuously measured by this device. The hematocrit was calculated using the formula, and the amount of fluid circulating in the body, which is inversely proportional to the hematocrit, was set in advance! If the water removal rate is made to match the Ej function, the water removal rate can be properly controlled by K.

The dialysate system 12 of the dialyzer 18 is provided with a well-known dialysate supply device 2, which supplies dialysate to the dialyzer 18 and forms a body circulating blood volume adjustment system in the dialyzer 1δ. Decompression in! 28 are connected. Transmembrane pressure is applied to the semipermeable membrane of the dialyzer 1g by reducing the pressure on the dialysate side by the vacuum inlet 28, and the water in the blood is transferred to the dialysate side through the semipermeable membrane. Ru. In this example, the reduced pressure is used! If the mechanical pressure difference across the semipermeable membrane in which S is generated is controlled by the control system 14 in accordance with the hematocrit value described above, the desired limit e is determined by K.
Overspeed is appropriately controlled according to the condition of each individual patient, allowing for optimal water removal without causing complications during liquid purification.

The control system 14 includes a control device 3 for controlling the reduced pressure index 2 based on the glue price of the hematocrit measuring device 24 and a predetermined fO duram, and a control device 3 for controlling the reduced pressure index 2@ based on the past record of the patient undergoing dialysis. Guarantee the favorable hematocrit changes in
The settings 53a are stored in Durham.

FIG. 2 shows the specific configuration of the hematocrit measurement S 4 described above, which is led into the blood introduction tube 1.
Resistance measurement unit 38 that measures the electrical resistivity of the liquid and further calculation WIA
Including 40.

The resistance measuring section 36 has a measuring cell 42 connected in communication with the introduction pipe 16, and electrical resistivity is measured by a four-electrode method. In this embodiment, the electrodes are arranged in a unique manner in order to eliminate the influence of resistivity caused by the flow of the internal fluid. That is, a pair of current electrodes 46 are connected to the insulation #44.
．． 4g and a pair of voltage electrodes 5G, 52 are arranged, and the current electrodes 46, 4B are arranged symmetrically with respect to the central axis of the insulating tube 44 and at nine positions separated by a predetermined distance in the direction of the central axis. , and the voltage electrodes sO%S2 are respectively provided in parallel inside the current electrodes 46, 41, and as a result, the resistivity of the blood in the diagonal direction with respect to the blood flow direction is measured. An AC constant current source 54 is connected to the current electrodes 4@, 48.
A measurement current is supplied from the voltmeter s6, and a voltmeter s6 is connected to the voltage electrodes 50 and 52 in order to detect the electrical resistivity of the blood at this time as a voltage value between the voltage electrodes 5G and 52, and its output is subjected to temperature correction s38. is supplied to.

In addition, the rounded and insulated tube 4 is corrected according to the temperature of the 16I liquid.
4 is a thermistor for temperature measurement! I8 is set to [1], and its output terminal is connected to temperature correction 11311.

In the present embodiment K, by employing the structure of the resistance measuring section 36 as described above, it is possible to eliminate the influence caused by the flow of blood. In other words, the -fluid consists of hypertrophic components and non-blood cell components, and in the frequency range from 1 KHz to IMHz, nine red corpuscles with an electrically insulating film were suspended in the hypertrophic fluid, which has a relatively high conductivity. It can be considered as a heterogeneous dielectric dispersion system. And red blood cells are biconcave disc-shaped and
The blood flow K creates a collection axis in which red blood cells are oriented, and as a result, the electrical properties of the blood are anisotropic and 5hear.
If rats is less than 3008, the electrical resistivity in the blood flow direction decreases and the electrical resistance in the direction perpendicular to the blood flow Kll increases, making it impossible to determine the correct hemadrit. Therefore, as described in the example, if the electrode arrangement is set obliquely to the blood flow and the electrical resistivity in the self-flow direction and in the oblique direction with a component perpendicular to this is measured, the blood Even if electrical anisotropy occurs due to the flow of the liquid, it is possible to cancel the effect and measure electrical resistivity equivalent to that of static white liquid gauze. In this embodiment, a current of 25K is supplied from the AC constant current source S4 in order to maintain safety for the human body and to avoid the influence of polarization.
HM, supplies a current of 304 Arms, and a friend voltmeter 5
6 converts the AC voltage into a DC voltage and supplies it to the temperature correction section 38.

The electrical resistivity obtained from the resistance measuring section 36 as described above is subjected to desired temperature correction by the 1i & correction section 311 based on the resistance value of the thermistor S8. Generally, in consideration of the fact that when the temperature rises by 1'C around the body temperature, the electrical resistivity decreases by about 2 degrees, temperature correction is performed to convert the electrical resistivity to the electrical resistivity at 37°C.

Historically, this temperature-corrected resistivity is calculated into hematocrit by calculation s4G. That is, 25K of blood
Electrical resistivity ρb (j'l -31) near Hg and centrifugation method to! Tocrit Ht(1) is however b
From Kl ';, 47, K, ; 1lt4f and coe, the hematocrit Ht is determined by hK, and the arithmetic unit 40 (includes a rounding attenuator @O and a logarithmic amplifier 62 to obtain the Shizuka equation).

The present invention is characterized in that the control system 14 controls the amount of blood circulating in the body using the hematocrit determined from the electrical resistivity of the blood as described above. 1*Example shown.

In this example, the setter 14, which stores the change in hematocrit, determines from the patient's past results and selects the desired amount of white fluid circulating in the body during dialysis. The embodiment includes a hemadcrit memory @6 for storing body fluid circulation.

The control device 30 has a configuration for driving and controlling the pressure reducing pump 28 of the dialysate system 12 based on the program of the hematocrit memory 66 and the measured value of the hematocrit analyzer 24.・A subtracter 68 that calculates the difference between the hematocrit during dialysis detected from the program and the hematocrit measurement @24, Ht, an integrator 7G that integrates the cough difference and generates a control @ signal, and an integrator. 70 and outputs drive power to the decompression bonder 28.

In the present invention, the itocrit Ht! If it is smaller than the program setting value, the driving power of the pump 28 is gradually increased and the hematocrit is reduced.) It! If the value is larger than the program setting value, the drive power of the I-amp 28 is controlled to be gradually decreased.

The first embodiment of the present invention has the above configuration, and its operation will be explained below.

Before starting white fluid dialysis, a program regarding the optimal hematocrit for the patient is set in the setting device 34 based on the patient's past dialysis records, weight gain from the end of the previous dialysis to the start of the current dialysis, blood pressure, and other patient records. recorded, this *Ks
Well-known hemodialysis is started.

In the present invention, during hemodialysis, the hematocrit is continuously determined, and the control system 12 is set as described above. Controls the water removal effect according to p grams.

Generally, in hemodialysis, dialyzer IIO semipermeable membrane KFJ
- The mechanical pressure on the liquid circulation circuit side, the mechanical pressure from the reduced pressure 17128, and the osmotic pressure of the blood and dialysate are added, and the desired ultrafiltration is performed by this. That is, by keeping the pressure of the dialysate lower than the pressure on the blood side, the water in the dialysate passes through a semi-permeable membrane to
Externally filtered.

At this time, the amount of water that is ultrafiltered per unit time is not comparable to the amount of water that moves from the body tissue into the own tube, and as a result,
Fluctuations occur in the amount of fluid circulating in the patient's body during hemodialysis. Normally, 1 kll dialysis (4 ~ @ hour S degree) on x eye □ 1 ~ SJI! O water removal is performed, and as a result of this O water removal, the amount of fluid circulating in the body decreases. The present invention is characterized in that the blood volume circulating in the body is controlled to be maintained at a predetermined programmed value at all times during liquid dialysis. Focusing on the fact that the blood volume circulating in the body is inversely proportional to hematocrit, the hematocrit was measured and compared with a predetermined program, and the
28 controls are performed.

Therefore, the 11th! In this example, when ultrafiltration is performed rapidly and the amount of fluid circulating in the body decreases rapidly, the hemadocrit at this time becomes larger than the set value, so the vacuum bomb f!
The ultrafiltration pressure of 8 is reduced to prevent a decrease in the amount of blood circulating in the body, and in the reverse case, the amount of circulating m-fluid is appropriately controlled as well. Therefore, by performing control according to such a predetermined program, water removal can be performed appropriately in accordance with the patient's condition.

FIG. 4 shows a second embodiment in which the present invention is applied to a lime juice filtration device, and the same members as those in the ls' embodiment are given the same reference numerals and their explanations will be omitted.

Blood filtration is performed by reducing the pressure of the hemofilter 74 and the drainage system 82 provided in the blood circulation system 10,
At the same time, the replenisher system 76 is added to the liquid circulation system 1G.
Replenishment fluid is supplied, purified, and Yuga fluid is returned to the patient's body. For this purpose, in this book, a discharge system I2 is provided for discharging the waste liquid that is treated by the hemofilter 14 of the liquid circulation system 1o, and its pressure is reduced to 1/f@4.
Pressure is generated in the semi-permeable membrane provided in the hemofilter 14, and ultrapolar treatment is performed.

9. The replenisher system 16 includes a replenisher supply device 1s and a supply pump 80 for supplying the replenisher to the blood circulation system 10, and in this embodiment, the replenisher system 1's supply pump 80 forms the body circulating am fluid volume ll1ilil system, and the control system 1
By changing the supply I blowfish 5ooa rotation number according to the control signal from 4, the liquid circulation is improved! By adjusting the amount of replenishment fluid supplied to the I system 1G, the amount of fluid circulating in the body can be controlled to a predetermined amount.

In this example, the white liquor circulation system! The replenisher system 76 is controlled by measuring the hematototal value in the white fluid and thereby adjusting the amount of circulating blood in the key body, but as in this embodiment, the replenisher system 76 is used to control electrolytes different from body fluids. If the electrolyte concentration and electrical resistivity of autologous plasma change, such as by injecting a large amount of concentrated replenishing fluid into the body, an error will occur if hematocrit Ht is determined from the electrical resistivity of blood alone (dynamic formula). Therefore, in this example, the electrical resistivity of blood is 4
The electrical resistivity ρp of the filtered waste liquid, which is a part of the Klkl plasma, is determined along with b, and the hematocrit Ht is determined from both electrical resistivities. For this purpose, in the blood circulation system 10, the hemofilter 7
The effluent of No. 4 is supplied to a hematocrit measuring device 24.

The figs show the Hemadcrit Fuchi measuring device 24 of the second example.
The configuration is shown.

As can be seen from FIG.
3-b, both of which have the same structure as in FIG. The electrical resistivity obtained from both resistance measurements 5113ε is calculated by the temperature correctors ssa, s and b of the temperature corrector 38.
After temperature correction is performed using 37° C. as a reference, the electrical resistivity of blood ρb and the electrical resistivity of one fluid 1'p are supplied to the calculation unit 40 to perform a desired hetcrit calculation. It will be done.

Here, in Equation (2) mentioned above, K is the electrical resistivity of blood when Ht==Q, so K,
is nothing but the electrical resistivity ρpK of own plasma. That is, Kt
=ρh becomes ρh.

In addition, there is a relationship between the change in electrical resistivity of blood at 9 o'clock when sodium chloride is added to normal blood (11b (jl on )) and hemadrit Ht (*), and the K island is It is known that Hoha is good.

Therefore, if the sodium chloride concentration in the blood deviates from the normal value for a healthy person due to liquid filtration or white fluid dialysis, 3
The relationship between the electrical resistance ρb of blood at 7° C., the electrical resistance ρp of autologous plasma at 37° C., and hematocrit generally holds the relationship of 1ζ41.

The calculation unit 40d calculates and outputs the hematocrit Ht from ρb and -p using this relationship.

That is, first, by the shift (b) path 111, (I of formula 4
' Find (54-βp) from p, attenuator SO, adder 9
2. By the calculation (b) path consisting of the squarer 94, multiplier 96, and attenuator S@, (from ρb(54-J'p) in equation 4, Jμ
), and then the hematocrit Ht is determined by the logarithmic amplifier 100.

As described above, when Ht is determined by taking into account the influence of changes in the electrolyte concentration in the solution due to filtration, the control system 14 operates based on this hematotalit HtK. The replenishment fluid system 76, which performs the same 4110 control action as in the embodiment and forms the body circulating fluid volume adjustment system in this embodiment, is controlled according to a predetermined program. The control device 32 of the third embodiment is the same except that an inverting amplifier 6 is provided between the subtracter 6 and the integrator 10.

The second and third embodiments of the present invention are comprised of the above-described configuration, and the operation thereof will be explained below.

In the second embodiment, 9 predetermined programs are stored in the hemocrit memory 66 according to the patient's condition before starting hemofiltration.
When blood filtration is started, the patient's fluid and ultrafiltrate are compared with this program, and the supply of replacement fluid is appropriately controlled.

That is, when the patient's internal circulating blood volume decreases significantly and the hematocrit H1 becomes larger than the predetermined program, the amount of replacement fluid injected is increased to compensate for the internal circulating blood volume, while the internal circulating *m* volume! This makes it possible to effectively remove excess water accumulated in the patient's body.

As mentioned above, in the 1st and 2nd embodiments, the hematocrit
By controlling the amount of fluid circulating in the body by Ht in a state suitable for each patient, it is possible to perform appropriate water removal without causing complications.

FIG. 7 shows a third practical example of the present invention, which is characterized in that, in the same way as in each of the above-described embodiments, the water removal amount is continuously measured along with the hemadcrit, and appropriate water removal control is performed using both of them. Hemodialysis is performed.

As is clear from the explanation of the second embodiment, when the electrolyte concentration in the blood changes due to blood purification, it is necessary to measure the hematocrit with high accuracy.In addition to the electrical resistivity of the blood, the electrical resistivity of the blood plasma is measured. Is required. On this point, Section S
In the first embodiment, the blood purifier 102 is used as in the first embodiment.
Round side pressure dialysate system separated from the source side by a semi-permeable membrane 1! Since the dialysate is supplied from the dialysate supply device 26 to perform the desired dialysis action, in order to keep the electrical resistivity of plasma constant, K is:
A 1oz blood purifier and a hematocrit purifier 24 are round hemofilters that separate a portion of blood from blood.
This provides the ultrafiltrate needed to keep the electrical resistivity of plasma constant.

Third! I! The internal fluid circulation system 10 of the example has its return pipe 2) K
Venous pressure regulators 1 and 4 are provided, and the pressure applied to the semipermeable membranes of the liquid purifiers 1 and 2 is adjusted by a signal from the control system 14, and this venous pressure regulator 1G4 adjusts the amount of fluid circulating in the body. forming a system.

When the hematocrit is measured in the internal fluid circulation system 1011'3, in the third example, the amount of water removed in the dialysate system 12 is kept constant, and Blood purifier 1020 Ultrafiltration rate measuring device t for detecting dialysate supply amount and drainage amount from the patient side and outlet side, respectively
The operating system (OS) is operated, and thereby the ultrafiltration amount is fixed based on the difference between the dialysate supply amount and the drainage amount, and this is used as the water removal amount signal in the control system 140 and the control device 3! supplied to

Figure 8 shows number 31! The configuration of the control system 14 in the embodiment is shown, and the setter 34 is provided with a water removal amount memory 1011 that stores a preferred water removal amount program during purification based on various records of the patient, separately from the hematocrit memory 66. A hematocrit grogram and a water removal grogram are separately supplied to the controller 32.

Then, the outputs of both memories 66 and 108 are respectively subtracted from the hematocrit and the limit P (amount of water removed) that are continuously measured during purification in subtracters ssa and 681, and both subtraction results are sent to adder 110. After being added, the signal is outputted as a control signal to the above-mentioned running pulse pressure regulator 104 via the integrator 7o and the amplifier 72.

The control system 14 of the third embodiment has the above configuration, and when the constant hematocrit and ultrafiltration rate during purification are smaller than the predetermined set values, the venous pressure regulator 104
The amount of ultrafiltration is controlled to increase by increasing the venous pressure of the liquid circulation system, and conversely, when each measured value is larger than the set value, the venous pressure is decreased to control the amount of ultrafiltration to be decreased.

Therefore, according to the third embodiment, efficient water removal can be performed without excessively reducing the microvolume blood volume in the patient's body, and O is measured during purification and the excess amount outside the limit is set at the set value. For pigeon lofts in which the measured value of hemocrit is larger than the set value despite the smaller K, the control to increase or decrease the ultrafiltration device is arbitrarily determined based on the difference between each measured value and the predetermined set value. The degree of consideration of hematocrit and ultrafiltration rate at this time is determined by the subtractor S a, 61bK in the example.
This can be done by applying appropriate weighting.

In each of the embodiments described above, the hemadcrit is directly input to the control system, but in the present invention, it is also possible to input the reciprocal of hemadcrit and other calculation results to the control system.

In addition, in each of the above-mentioned embodiments, as a means for stably measuring the volume of rounding and circulating liquid for controlling the high degree of self-circulation in the body, H! Although the tocrit constant is used, in the present invention, it is also possible to calculate the circulation surface number minute change from the change in the concentration by calculating the constant rate in addition to the rate.

In addition, by measuring the amount of circulating JjlrIR fluid using this osmotic pressure, a minute pressure difference (31 to 351 @H#) is detected through the semipermeable membrane.
must be measured, and the characteristics of the semipermeable membrane must be strictly determined.

As explained above, according to the present invention, the amount of fluid circulating in the body of a patient during internal fluid purification is continuously measured, and thereby a predetermined amount suitable for the patient is determined. Water removal speed can be automatically controlled according to the program, making it possible to perform efficient water removal while maintaining the body (internal circulation #1 - fluid volume in an optimal state).

[Brief explanation of the drawing]

Fig. 1 is a block circuit diagram showing a preferred first embodiment of the internal fluid purification device according to the present invention, Fig. 2 is an explanatory diagram showing a hematocrit measuring device of the 1s example, and Fig. 3 is a first embodiment. A block circuit diagram of the control system in the example, FIG. 4 is a plotter circuit diagram of the second embodiment of the present invention, FIG. A block schematic diagram showing the control system of the embodiment, FIG. 7 is a plotter circuit diagram of the third practical example of the present invention, and FIG. 8 is the sli! It is a famic road diagram showing a control system in an example. 10...-Liquid circulation system, l! ...dialysate system, 14
...Control system, l$...Dylyzer, 24...Hematocrit measuring device, 28...Reducing pressure Inf, 112-...Control device, 34
...Setter, 3...Resistance-Ube, 42.
...Measurement cell, 44...Insulation tube, 46.48.
...Current electrode, 50%s2...Voltage electrode, 54...AC constant current source, s6...Voltage needle, 66...
・Hematocrit meter, 74...Hemofilter, 1...Replenisher system, @O・
・・Supply 47f, 1・2・・Liquid purifier, 104
... Venous pressure regulator, 101i... Ultra-e excess amount-j regulator, 10g... Water removal amount memory.

Claims (1)

[Scope of Claims] (1) A white fluid circulation system that circulates the patient's own fluid outside the body; and - liquid purification through dialysis or filtering through a semipermeable membrane provided in the fluid circulation system. A white liquor purifier that controls the water removal rate, an internal fluid volume adjustment system that adjusts the internal fluid volume to a desired value by controlling the water removal rate, and a circulation system that measures changes in the internal fluid volume. ll
- Equipped with a fluid volume meter and a fluid volume memory that stores a log of fluid volume changes in the body during fluid purification according to the patient's condition, and is measured during fluid purification. body circulation lI
It is characterized by including a control system that controls the internal circulation 3J internal fluid volume adjustment system based on the internal fluid volume and a predetermined 1 log, and performs an optimal water removal action while maintaining the internal circulating S internal fluid volume at a desired value. White liquor purification equipment. In the apparatus according to claim (1), the circulating blood volume column measuring device comprises a hematocrit measuring device that detects changes in the amount of blood circulating in the body based on changes in hematocrit. Device. (3) In the device according to claim (2),
The hematocrit analyzer consists of a resistance measuring section that measures the electrical resistivity of the calyces fluid circulation system, a temperature correcting section that compensates for the measured electrical resistivity with temperature, and a calculating section that calculates the hematocrit from this electrical resistivity. The resistance measuring unit further includes at least a pair of electrodes provided on the insulating tube connected to the surface circulation system on the symmetric side with respect to the central axis thereof and nine positions apart by a predetermined distance in the direction of the central axis. A white liquor purification device characterized by having a measurement cell having: (4) Claims (In the apparatus described in the plow, the resistance measuring section is provided with a measuring cell for measuring the electric resistivity of the self-containing components in the liquid; A liquid purification device characterized in that the hematocrit is calculated from both the electrical resistivity of The electrical resistivity of the self-contained components is reduced to 11 by installing the filter in the filtration waste liquid path of the filter.
A blood purification device characterized in that it is provided with a measurement cell for determining blood purification. (匈) In the device according to any one of claims (1) to (5), a dynamic pressure difference is generated by sandwiching the semipermeable membrane of the intracorporeal circulating fluid volume adjustment system t'i fluid purifier. (7) In the device according to any one of claims (1)-4, the body circulating blood volume regulating system supplies a replenishing fluid to the white fluid circulation system. A blood purification device characterized in that it includes a replenishment fluid system for supplying blood.(~Claim f1) In the device according to any one of ~ functions, the body circulating blood volume adjustment system is a semipermeable membrane of the stroke purifier. and a means for injecting a replenisher into the MS circulation system, and the control system controls at least one of the mechanical pressure difference generating means and the replenisher injecting means. -Liquid purification device. (-A self-circulation system that circulates the patient's blood outside the body, a T-liquid purifier installed in the white liquor circulation system, and a t-liquid purifier that controls the water removal rate to control the blood circulating in the body. Body circulation m- to adjust the amount to the desired value K11lI
Fluid volume adjustment system, blood circulation in the body - water removal measuring device that measures the amount of water, and body circulation during blood purification depending on the patient's condition.
White liquid amount change! Internal circulation blood volume memory that stores the program and amount of water removed that stores the amount of water removed! It has a program that determines the amount of blood circulating in the body and the amount of water removed that is measured during liquid purification! 1. A blood purification device comprising: a control system that controls a body circulating blood volume adjustment system by comparing the blood volume with a blood purification system, and performs an optimal water removal action while maintaining a body circulating blood volume at a desired value.