JPS6125564A - Artificial kidney 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] [Technical field to which the invention pertains] This invention relates to an artificial kidney device that performs dialysis or filtration of blood, and mainly relates to an artificial kidney device that performs dialysis or filtration of blood. The present invention relates to an artificial kidney device system configured to effectively prevent clogging.

[Prior art and its problems]

Conventionally, in blood dialysis, diafiltration, and hemofiltration, semipermeable membranes have been used for these dialysis or filtration processes, and the ultrafiltration action of this membrane allows blood water on the blood side to be transferred to the dialysate or filtration wire. Water is removed from the side trap. In this case, in conventional dialysis or filtration methods, the saving pressure on the normal blood side is maintained higher than the pressure on the dialysate or R-line side, and the direction of movement of blood water is always from the blood side to the dialysate or R-line side. It is directed. For this reason, proteins in the blood adhere to the pores of the membrane that defines the blood side and the dialysate or R-ray side, causing clogging, and the water removal ability of the membrane decreases over time. .

Furthermore, although dialyzers or filters equipped with this type of membrane are very expensive, there is a risk of infection such as serum hepatitis when they are used for blood purification of multiple people. For some reason, all parts, including blood-related parts, are forced to be disposable once per person.

From this point of view, the pressure on the dialysate or filter wire side is made relatively higher than the pressure on the blood side, and the direction of movement of the fluid relative to the membrane is reversed. Methods have been proposed to ensure long-term use of filters or filters.

However, in general, when blood system components come into contact with blood, fibrin adhesion and blood coagulation occur in blood flow retention areas and system expansion areas, making cleaning after treatment difficult. Therefore, if the device is reused after incomplete cleaning, the deposits and coagulation may peel off and flow into the body, potentially occluding blood vessels, which is extremely dangerous.

Therefore, we aim to replace blood system parts as cheaply as possible,
In order to improve the operating rate of artificial kidney devices in hospitals and the like, it is necessary to clean dialyzers or filters completely aseptically. Therefore, as a means for effectively backwashing the membrane as described above, there is a fluid passage pressure forming means that makes the pressure on the P line side relatively higher than the pressure on the blood side, and for example, the pressure on the membrane on the dialysate side is By providing a supply pump and a delivery pump on the inflow side and the outflow side, respectively, and making the delivery amount of the delivery pump relatively larger than the delivery amount of the supply pump,
A method has been proposed in which fluid is passed from the P line side to the blood side.

However, in this type of backwashing method, 1. In this case, the flow velocity in the blood-side flow path increases rapidly, and the pressure within the flow path rises rapidly, leading to the risk of the flow path becoming disconnected or impacting the living body, which poses many operational problems.

[Purpose of the invention]

The object of the present invention is to expand an artificial kidney that can effectively and efficiently backwash membranes in dialyzers or h-filters with a relatively simple configuration, and can be handled safely even for living organisms through simple operation. We are in the process of providing equipment.

[Key points of the invention]

The artificial kidney device according to the present invention purifies blood by providing a dialyzer or a filter that defines a blood system and a dialysate or r-liquid system via a semipermeable membrane or a filtration membrane. In the apparatus, a reservoir equipped with a load meter is connected to the blood system and the dialysate or r-liquid system through reversible liquid feeding means, respectively, and by switching the reversible liquid feeding means to the reverse feeding, the inside of the dialyzer or filter is connected. The percentage image is that the membrane is configured to be alternately subjected to dialysis treatment and backwashing by changing the pressure conditions of the membrane.

In the artificial kidney device described above, the load cell butterfly provided in each reservoir is configured to set upper and lower limits of the amount of liquid stored in the reservoir, and to perform switching control of the reversible liquid feeding means at the limits of these set liquid amounts. It is suitable if

In addition, the dialysate system is a top-class structure having a liquid supply means and a delivery means on the inflow and outflow sides of the dialyzer, respectively, and a water removal system equipped with a water removal pump between the dialyzer and the delivery means. At the same time, the dialysate reservoir is connected in a branch manner via a reversible liquid feeding means. It also constitutes a P liquid system. In that case, P
A liquid system is led out from the filter through a water removal pump, a fluid replacement system is connected through an outflow flK fluid replacement pump of the blood system filter, and a reversible liquid feeding means is provided between the filter and the water removal pump. Connect the liquid reservoir to the branch via.

Furthermore, the blood system is constructed by connecting a liquid pump to the inflow side of the dialyzer or filter and branchingly connecting a blood reservoir to the outflow side via a reversible liquid feeding means.

[Embodiments of the invention]

Next, an embodiment of the artificial kidney device according to the present invention will be described in detail below with reference to the accompanying drawings.

FIG. 1 is a system diagram showing the principle of the apparatus of the present invention. That is, in FIG. 1, the reference numeral IO indicates a dialyzer or filter (hereinafter simply referred to as a dialyzer) in which the blood side and the dialysate or P line side are defined by a semipermeable membrane (F membrane) lλ.
shows.

This dialyzer IQ has blood system/g and dialysate (P), respectively.
The blood system 16 is connected in communication with the blood system 16, and the blood system 16 is provided with a blood pump P6, and the dialysate system 6 is provided with a fluid supply pump Pδ as a fluid supply means and a delivery pump P4 as a delivery means.

However, in the present invention, a reversible pump P+ as a reversible liquid feeding means is provided on the outflow side of the dialyzer 10 in the blood system l≠.
The blood reservoir/If is branch-connected via the dialysate system/A, and the dialysate reservoir Paco 0 is branch-connected to the outflow side of the dialyzer 10 of the dialysate system/A via a reversible pump P2.

By the way, in an artificial kidney device that normally has this polar system configuration, K, which achieves backwashing from the dialysate (P fluid) side to the blood side via W/K, is, for example, as shown in Fig. 2. The inflow amount from the dialysate side to the blood side in the device 10 is q'
Then, the amount of liquid QB2 flowing out from the dialyzer io is Q[12==Qn+ + q'
becomes.

Therefore, in the present invention, as described above, the blood system l≠ and the dialysate system 16 have reservoirs /I, 2, respectively.
0 and is configured to appropriately store the backwash flow t.

Therefore, in the apparatus of the present invention configured as shown in FIG.
5 and the delivery pump P4 form a closed system, and the internal pressure of the closed system is increased by the flow of fluid from the dialysate reservoir 20 into this closed system by the pump P2, and the closed system is increased by the flow of fluid from the dialysate reservoir 20 into the closed system by the pump P2. The outflow of fluid from the dialyzer 10 reduces the internal pressure of the closed system and generates a fluid flow 9.9' through the membrane 7.2 of the dialyzer 10. Therefore, the blood stored in the blood reservoir /A is caused to flow out into the blood system l≠ by operating the pump P1, while the dialysate supplied to the dialysate system /A is transferred to the dialysate reservoir O by operating the pump P2.
If stored in the dialysis chamber, smooth dialysis treatment can be achieved. In addition, the dialysate stored in the dialysate reservoir 〇 is caused to flow out to the dialysate system/6 by operating the pump P2, while the blood being supplied to the blood thread 1 is stored in the blood reservoir by operating the pump P+. Then, backwashing with the dialysate through the membrane 12 can be effectively achieved.

In this case, if the discharge volume of the pumps p, , pg and P4 that control the flow of each liquid in the blood system/4t and the dialysate system 16 is set to a predetermined value, communication with each reservoir l♂, 20 will be established. Safe backflow can be achieved simply by reversibly operating the pumps P+ and r'2 connected to the system.

In other words, during dialysis and backwashing, the blood system/4' dialyzer 10
The blood flow rate QB2 returned to the body via the dialyzer IO
A stable flow rate is always obtained without being affected by internal pressure changes, allowing safe treatment.

However, when actually operating the device of the present invention having the above configuration, the lines, blood system/4 (and pumps PI, P connected to the reservoirs L♂, 20 provided in the dialysate system 16)
It is necessary to appropriately control the operating direction and flow rate of the second method. Therefore, in the present invention, as shown in FIG. 3, load cells 22. ．． 2. A load cell is provided so that the upper and lower limits of the amount of liquid that can be stored in each reservoir /I and /O can be set. It is configured to perform reversible switching control of pumps PI and P2 under the action of J$. As shown in Fig. 3, a water removal system roller equipped with a water removal pump P5 is connected to the dialysate system in order to discharge the amount of water removed from the blood side which is mixed with the amount of fluid q flowing out to the dialysate side during dialysis. l Connected to a part of B.

Therefore, the operation of the embodiment shown in FIG. 3 will be explained. To simplify the explanation, assuming that the operation of the water removal pump P5 is stopped and the discharge volume of the fluid supply pump P3 and the delivery pump P4 of the dialysate system 16 are the same, the fluid volume of the blood system /F is assumed to be the same. keQIII=QBz. In this state, the dialysate is stored in the dialysate reservoir O in advance to the upper limit of 2.2, while the blood reservoir/IK is set to the lower limit of 2.2. , pump P1 has a discharge amount Q'(P+)'', and pump P2 has a discharge amount Q'(p+)''.
2) (However, if you operate at the same time with "(P+) = "(P2)) and backwash the membrane as explained in Figure 1, the blood will be returned to the body via the dialyzer io in the blood system l≠. Backwashing of the membrane can be achieved without any change in the amount of liquid QB2.

Next, when the storage amount of the blood reservoir/I reaches the upper limit of the load cell 1 and the storage amount of the dialysate reservoir θ reaches the lower limit of the load cell 1, if each of the pumps PI and P2 is reversed, Blood dialysis treatment can be performed. In addition, at this time, the water removal pump P5 is operated, and the fluid supply pump p of the dialysate system 16 is operated.
By appropriately adjusting the discharge amount of pump P4 and/or the delivery pump P4, it is possible to easily achieve the total amount of water removed from the needle side during dialysis treatment.

Further, as the load cell used in this embodiment, a load cell, a differential transformer, a spring scale, a balance, etc. can be appropriately employed.

FIG. 4 shows an embodiment in which the present invention is applied to a P-type artificial kidney device. In addition.

For convenience of explanation, components common to the embodiment shown in FIG. 3 are given the same reference numerals, and detailed explanation thereof will be omitted. However, as shown in FIG. Water is removed through the membrane /, 2, and this r liquid is converted into r liquid v.
It will be collected on i32. On the other hand, a fluid replacement system 3≠ equipped with a fluid replacement pump P7 is connected to the blood system/g on the outflow side of the filter 10,
The replacement fluid amount is slightly smaller than the removed p fluid amount under the action of the irB fluid pump P7! Supplied from a36. Therefore, in this embodiment, as in the previous embodiment, a blood reservoir IT equipped with a load cell 2.2 is branch-connected to the outflow side of the blood system filter IO via a reversible pump P1. A P liquid reservoir 20 equipped with a load meter, 2μ, is branched and connected via a reversible pump P2 between the connection of the f=I filter 10 of the liquid system 3θ and the water removal pump P5.

Next, the operation of this embodiment will be explained. First, operating conditions are set for the blood pump Pi, the water removal pump P5, and the replacement fluid pump P7 so that they are appropriate and capable of water removal. Therefore, as in the above embodiment, blood reservoirs l♂ and P
Each liquid reservoir O holds a predetermined amount of liquid,
By operating the reversible pumps PI, P2, backwashing of the membrane 12 can be effectively achieved without changing the amount of liquid Q B2 / returned to the body of the salmon through the filter 10.

〔Effect of the invention〕

As is clear from the various embodiments described above, according to the present invention, backwashing of the membrane is achieved while maintaining the amount of fluid returned to the body through the blood dialyzer at a constant state. Therefore, even if, for example, dialysis or filtration operation is rapidly switched to reverse operation, there will be no disconnection of the system or shock to the living body, and safe and effective backwashing can be realized.

Furthermore, according to the present invention, the basic configuration of the system can be modified by simply adding a system consisting of a reservoir equipped with a load cell for storing each group of fluids and a reversible fluid transfer means to a conventional artificial kidney device. Since it is not a standard product, it can be immediately applied to existing equipment, can be manufactured at low cost, and is easy to maintain.

Therefore, even when reusing a dialyzer (filter) by repeating backwashing, for example, by using roller pumps for all the various fluid delivery means and pumps, and using a low-cost reservoir, the blood system can be improved. Replacing parts can also be achieved very economically.

Although the preferred embodiments of the present invention have been described above, it goes without saying that various design changes can be made without departing from the spirit of the present invention.

For example, as the reversible liquid feeding means, the liquid supplying means and the delivery means that form a closed system for dialysate to the dialyzer, any means capable of controlling liquid feeding, such as a pump, may be used.

[Brief explanation of the drawing]

Fig. 1 is a system diagram showing the basic principle of the artificial kidney device according to the present invention, and Fig. 2 is an explanatory diagram showing the relationship between the liquid flow between the blood system and the dialysate system due to backwashing of the dialyzer shown in Fig. 1. , FIG. 3 is a system diagram showing one embodiment of the artificial kidney device according to the present invention, and FIG. 3 is a system diagram showing another embodiment of the artificial kidney device according to the present invention. IO...Dylyzer (filter) /λ...Semi-permeable membrane (filtration membrane) Ig...Blood system 16...Dialysate system/
lr...blood reservoir λO...dialysate reservoir 22.217...loading needle, 2J...water removal system 3Q...P liquid system 3.2...r liquid storage tank 3
G... Replacement fluid system 36... Replacement fluid storage tank PI,
P2...Reversible pump P5...Liquid supply pump P4...Delivery pump P5
... Water removal pump P6 ... Blood supply pump P7
...Fluid pump

Claims (5)

[Claims] (1) In an artificial kidney device that purifies blood by installing a dialyzer or filter that defines the blood system and the dialysate or filtrate system via a semipermeable membrane or filtration membrane, A reservoir equipped with a load meter is connected to the filtrate system through a reversible liquid transfer means, respectively, and the pressure conditions in the dialyzer or filter are changed by switching the reversible liquid transfer means to reverse the flow of the membrane. An artificial kidney device characterized in that it is configured to alternately perform diafiltration and backwashing. (2) In the artificial kidney device according to claim 1, the load cell provided in each reverser sets the upper and lower limits of the amount of liquid stored in the reservoir, and the reversible liquid transfer is performed at the limits of these set amounts of liquid. An artificial kidney device configured to perform switching control of means. (3) In the artificial kidney device according to claim 1, the dialysate system is provided with a fluid supply means and a delivery means on the inflow side and the outflow side of the dialyzer, respectively, and between the dialyzer and the delivery means. An artificial kidney device comprising: a water removal system equipped with a water removal pump connected to the dialysis fluid reservoir; (4) In the artificial kidney device according to claim 1, the filtrate system is led out from the filter via a water removal pump, and the fluid replacement system is connected to the outflow side of the blood system filter via a fluid replacement pump. and a liquid reservoir is branch-connected between the filter and the water removal pump via a reversible liquid feeding means. (5) In the artificial kidney device according to claim 1, 3, or 4, a fluid feeding pump is connected to the inflow side of the dialyzer in the blood system, and a reversible fluid feeding means is connected to the outflow side of the dialyzer. An artificial kidney device with blood reservoirs connected in branches.