JP2007222668A - Hemodialyzer - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide an automatic priming device, surely keeping a priming liquid in a clean state at the start of hemodialysis while maintaining satisfactory circuit cleaning and air elimination performance. <P>SOLUTION: In this hemodialyzer, the upstream end of an artery blood circuit 2 and the downstream end of a venous blood circuit 3 are connected to each other to form a blood circulation circuit, a dialysis fluid is injected into a dialysis fluid circulation circuit 6 from outside of a system through a dialysis fluid injection circuit 7, the dialysis fluid is caused to flow into the blood side from the dialysis fluid side through a hollow fiber membrane of the hemodialyzer 1, and while the flow-in dialysis fluid is circulated through the blood circulation circuit by the blood pump 14, surplus flow-in dialysis fluid is caused to overflow from a residing liquid external discharge circuit 5, and after only a predetermined liquid quantity is circulated through the blood circulation circuit, inflow of dialysis fluid from the dialysis fluid injection circuit is stopped. Instead of it, transfusion is injected from a transfusion injection circuit 4 to discharge a residing dialysis fluid in the blood circulation circuit from the residing liquid external discharge circuit 5, and the dialysis fluid in the blood circulation circuit is replaced with transfusion injected from the transfusion injection circuit 4. <P>COPYRIGHT: (C)2007,JPO&INPIT

Description

The present invention relates to a hemodialysis apparatus that is simple in washing operation of a dialyzer and good in washing performance. In particular, the present invention relates to a hemodialysis apparatus excellent in cleanliness of a priming solution entering a dialysis patient.

  In hemodialysis treatment using a hollow fiber membrane hemodialyzer, the part where blood circulates before the start of treatment, that is, the inside of the dialyzer hollow fiber membrane, the arterial blood circuit and the venous blood circuit (hereinafter these three members are connected) An operation called priming is performed in which the priming liquid is filled and replaced while flushing out air in the blood circuit. This priming is for washing out the foreign matters remaining on the inner surface of the circuit in contact with the blood, thereby preventing foreign matters from entering the body and preventing blood from being dissolved by contact with the foreign matters. At the same time, all the air present in the hollow fiber membrane and blood circuit is expelled to prevent air from entering the human body. Note that the priming liquid remaining in the circuit after the priming operation is returned to the human blood and requires a high degree of cleanliness.

This priming operation requires a great deal of labor and time for the medical staff because the air in the blood circuit is completely expelled by the priming liquid while the inner surface of the blood circuit is cleaned. This is because the presence of even minute air (bubbles) may cause a serious medical accident such as blocking blood flow (infarction) when mixed with human blood. .
Therefore, before inserting the needle at the tip of the arterial blood circuit and the venous blood circuit into the patient's blood vessel, the medical staff inserts the needle of the arterial blood circuit into the infusion bag, opens the venous blood circuit, and hemodialyzes while flowing the infusion into the blood circuit. The blood circuit is frequently closed and opened with forceps, and the air bubbles are completely expelled from the venous blood circuit by the pressure shock.

  More generally, even if the arterial blood circuit and the venous blood circuit are dry (no filling liquid), a wet type filled with a filling liquid is widely used in hemodialyzers. There is provided a dry type hemodialyzer having no filling liquid inside and outside. In this case, a large amount of air is present inside the hollow fiber membrane, but the above operation is made more difficult because it is difficult to escape.

  In particular, hemodialysis is started for a large number of patients at the same time, requiring not only technical difficulties but also promptness, and the burden on medical staff in connection with ensuring medical safety. Is tough.

  In order to improve this, an endotoxin cut filter is installed in the dialysate supply circuit, the dialysate that has permeated the filter is back-filtered from the outside to the inside of the hollow fiber membrane, and priming is performed, so that the operation is performed. An automated apparatus has been proposed (Patent Document 1).

However, such an apparatus not only requires an expensive device called an endotoxin cut filter, but this priming solution is clean when the endotoxin cut filter is not sufficiently managed or a hollow fiber membrane leak occurs. There is a serious potential risk that priming fluids that are not clean will be mixed into the body.
Japanese Patent No. 2979234

  The present invention is intended to provide an automatic priming device that maintains a sufficient circuit cleaning property and air evacuation property and at the same time ensures that the priming solution at the start of hemodialysis is kept clean.

  The hemodialysis apparatus of the present invention that achieves such an object has the following configuration.

That is, a hollow fiber membrane hemodialyzer, an arterial blood circuit connected to the inflow side of the blood circuit so as to circulate inside the hollow fiber membrane of the dialyzer, and a venous blood circuit connected to the outflow side, An infusion infusion circuit connected in the middle of the arterial blood circuit, a blood pump installed between the dialyser from the junction of the infusion infusion circuit and the arterial blood circuit, and a staying fluid branched from the middle of the venous blood circuit An outside drain circuit, a dialysate circulation circuit in which a dialysate substantially circulates outside the hollow fiber membrane in the dialyzer, and a dialysate circulation circuit formed from outside the system in the middle of the dialysate circulation circuit A dialysate injection circuit for supplying a new dialysate, and a blood circulation circuit is formed by connecting the upstream end of the arterial blood circuit and the downstream end of the venous blood circuit; Dialysate from outside The dialysis fluid is poured into the blood flow side from the dialysis fluid side through the hollow fiber membrane of the dialyzer and injected into the analysis fluid circulation circuit, and the dialysis fluid is circulated in the blood circulation circuit with the blood pump. , The excess inflow dialysate overflows from the staying fluid system drain circuit, and after circulating through the blood circulation circuit by a predetermined amount, stops the inflow of dialysate from the dialysate injection circuit, instead The infusion fluid is injected from the infusion fluid injection circuit, the retained dialysate in the blood circulation circuit is discharged from the retention fluid outside drain circuit, and the dialysate in the blood circulation circuit is injected into the infusion fluid injected from the infusion fluid injection circuit. It is a hemodialysis apparatus configured to be replaced, and more preferably, the dialysis apparatus has a venous blood clamp provided in the middle of the venous blood circuit .

  According to the hemodialysis apparatus of the present invention, a large amount of dialysate is allowed to flow from the outside to the inside of the hollow fiber membrane in the hemodialyzer, so that a sufficient cleaning effect on the inner surface of the blood circuit can be obtained. Air evacuation is also good due to the increased flow rate.

  Furthermore, after circuit cleaning and air exclusion, it is replaced with a clean infusion solution (generally, saline), so that an expensive endotoxin cut filter with no guarantee of cleanliness as found in conventional methods is produced. The dialysate is not mixed into the body.

  According to the present invention, washing of the blood circuit and air discharge in the circuit can be performed automatically in a short time and without human intervention, and by replacing with physiological saline prior to dialysis treatment, It is possible to maintain the cleanliness of the circuit staying liquid introduced into the circuit.

Hereinafter, the hemodialysis apparatus of the present invention will be described in more detail based on the drawings and the like.

  FIG. 1 is an overall schematic diagram of a hemodialysis apparatus according to the present invention.

  2 to 5 are model diagrams for explaining the operation steps of the hemodialysis apparatus according to the present invention.

  FIG. 6 is an overall schematic diagram illustrating another embodiment of the hemodialysis apparatus according to the present invention.

  In FIG. 1, about 10,000 hollow fiber membranes are accommodated in a hollow fiber membrane hemodialyzer 1. Through the hollow fiber membrane, blood flows inside the hollow fiber and dialysate flows outside. During dialysis, the arterial blood circuit 2 is punctured into the patient's brachial artery by an arterial needle (not shown) attached to the tip of the connector A (the upstream end of the arterial blood circuit), and is introduced into the dialyzer 1 through the arterial blood circuit 2. .

  The blood purified by dialysate through the hollow fiber membrane in the dialyzer 1 passes through a venous blood circuit 3 and a venous needle (not shown) attached to the tip of the connector B (downstream end of the venous blood circuit). Returned to patient brachial vein.

  In the infusion solution injection circuit 4, the infusion solution (generally physiological saline) in the infusion bag 11 is injected into the inlet C point of the blood pump 14 of the circuit 2 through the infusion breakage detector 12 and the infusion clamp 13. . Reference numerals 15 and 16 denote drip chambers provided in the arterial blood circuit and the venous blood circuit, respectively, where air bubbles are temporarily captured and the internal pressure thereof is monitored by PS (Pressure Switch: pressure switch).

  In the upper part of the venous blood circuit drip chamber 16 in the venous blood circuit, a drainage system outside drainage circuit 5 is provided, and a drainage liquid clamp 17 is installed in the middle thereof. Further, a bubble detector 18 and a venous blood clamp 19 are provided in the venous blood circuit 3 from the drip chamber 16 to monitor and prevent air from entering the patient in the event of an emergency.

  The dialysate circulation circuit 6 is connected to the dialysate inlet and outlet of the dialyzer 1. For example, the equalization chamber 20 and the liquid feed pump 21 described in Japanese Patent Publication No. 1363767 form a substantially closed circulation circuit. ing. A flexible diaphragm 22 is accommodated in the chamber 20, and a completely dialyzed solution equivalent to the fresh dialysate sent from the chamber 20 to the dialyzer 1 flows back to the opposite side of the chamber 20. Actually, two chambers 20 are provided, and are operated continuously by switching alternately. A fresh dialysate injection circuit 7 from the outside of the closed circulation circuit is connected to the dialyser 1 inlet side of the dialysate circulation circuit 6, and a shutoff valve 23 and a pressure control valve 24 are installed in the middle of the circuit.

  Next, the operation will be described with reference to FIG.

  FIG. 2 is Step 1 regarding the priming operation. First, after connecting the connectors A and B, the clamps 13, 17 and 19 are opened while the blood pump 14 is stopped. Then, the physiological saline in the infusion bag 11 is filled into the circuit 4 by natural dropping. Step 1 ends when the circuit 4 is almost full.

  In step 2 of FIG. 3, the clamp 13 is closed and the supply of physiological saline is stopped. Instead, the blood pump 14 operates.

  Furthermore, the dialysate pump 21 is operated, and the dialysate flows in the circuit 6. At the same time, the shut-off valve 23 is opened, and the dialysate having the pressure set via the pressure control valve 24 is injected from the circuit 7. Since the circuit 6 is substantially a closed circulation circuit as described above, the dialysate injected from the circuit 7 moves to the blood side through the hollow fiber membrane in the dialyzer 1. Since the blood pump 14 is driven, the dialysate fills the whole blood circuit while flowing through the dialyzer 1, circuits 3 and 2 in the direction of the figure in the direction of the arrow. At first, the air in the circuits 3 and 2 is pushed out from the circuit 5 and discharged, but after almost the whole amount is discharged, the dialysate supplied from the circuit 7 is continuously discharged as surplus dialysate. It will be.

  After the air in the blood circuit is sufficiently exhausted, the process proceeds to step 3 in FIG. 4, but the shutoff valve 23 is closed and the supply of dialysate from the circuit 7 is stopped. Accordingly, the dialysate does not flow to the blood circuit via the hollow fiber membrane. The clamp 19 is closed. Instead, the clamp 13 is opened again, and physiological saline is drawn from the circuit 4 by the blood pump 14, and the staying dialysate in the blood circulation circuit is located downstream of the arterial blood circuit 2, as indicated by the arrow, on the dialyzer 1. The fluid is discharged from the circuit 5 through the upstream side of the venous blood circuit 3.

  When the circuit described above is replaced with physiological saline, the process proceeds to step 4 in FIG. At this time, the blood pump 14 is stopped and the clamp 19 is opened instead. Therefore, as shown by the arrows, physiological saline flows to the upstream side of the blood circuit 2, the connectors A and B, the downstream side of the blood circuit 3, and the circuit 5, and is replaced with the dialysate used for priming.

  By these steps 3 and 4, the staying dialysate in the whole blood circuit is replaced with the whole amount of physiological saline. Next, for example, the clamps 13, 17 and 19 are closed, and the dialysis process is waited. Is.

  The amount of dialysate circulated by the blood pump is set in advance, which depends on the ease of washing of the dialysate and the flow rate of the dialysate flowing from the dialysate side to the blood side. Usually, the amount of dialysate to be introduced is about 1 L, but in a dialyzer with poor cleaning performance, a larger amount of dialysate is introduced to improve the cleaning performance. The amount of the circulating dialysate may be monitored by the total discharge amount of the blood pump 14 or can be defined by the operation time if the blood pump flow rate is set to 300 ml / min, for example. Further, if a metering pump is used in place of the shutoff valve 23 and the pressure control valve 24 and the operation time thereof is restricted, the amount of dialysate injected into the dialysate flow circuit 6 from outside the system can be accurately defined.

  In addition, the amount of physiological saline to be replaced is based on the total internal volume of the dialyzer 1, the arterial blood circuit 2 and the venous blood circuit 3, and it is not preferable for the purpose of the present invention to be significantly less than that. Since the fluid replacement can be performed in a piston flow manner, physiological saline is not used more than necessary.

  Hereinafter, another embodiment of the present invention will be described.

  That is, as another aspect, it is possible to circulate dialysate in the blood circulation circuit after step 2 in FIG. 3 without moving to step 3 in FIG. 4 and with the shut-off valve 23 closed.

At this time, it is effective to shut off and open the clamp 19 in the venous blood circuit 3 at intervals of 1 to 5 seconds 30 times or more. The number of repetitions is determined from the time required for the bubbles present in the blood circulation circuit to make a round in the circuit. For example, when the opening / closing time of the clamp 19 is T, the number of opening / closing operations is F, the capacity of the whole blood circulation circuit (including the dialyzer 1) is V, the amount of liquid delivered by the blood pump 14 is Q, and the opening / closing is F, It becomes a standard.
F = V ÷ (T × Q)
Due to the pressure vibration generated when the clamp 19 is opened and closed, the evacuation property of the air in the circuit can be remarkably improved.

  The combination of the bubble detector 18 and the clamp 19 is normally installed in order to prevent air from entering a patient in normal dialysis, and a special device for promoting air discharge is necessary. Not. Further, since this combination is installed after the drip chamber 16, the pressure shock due to opening and closing is relieved, and there is no possibility that the hollow fiber membrane in the dialyzer 1 is damaged and leaked.

  Further, as shown in FIG. 6, the effect of the present invention is further improved if the connection point C between the circuit 4 and the circuit 2 is immediately after the connector A connected to the arterial needle. This is because the blood remaining in the circuits 2 and 3 and the dialyzer 1 must be returned to the patient at the end of dialysis. At this time, in order to avoid air contamination, extrusion with physiological saline from the infusion bag 11 is instructed, but if the junction C is immediately after the arterial needle, the staying blood between the arterial needle A and the junction C The recovery is negligible.

  This is because, for example, if the distance between A and C is 5 cm, it will not be as small as 1 ml. Conventionally, since the point C is far from the arterial needle, it has been necessary to return the arterial blood to the artery side, contrary to the normal flow. However, since thrombus is likely to occur in the arterial circuit, it has been pointed out that this thrombus may be returned to the patient's artery and cause a medical accident.

  In this embodiment, the discarded blood between A and C is less than the amount used for blood collection for blood analysis, and is not a problem level. At this time, as shown in FIG. 6, the arterial blood circuit 2 and the infusion circuit 4 located upstream of the connection point C have an arterial blood circuit capable of crushing and closing the circuit (generally a flexible PVC tube). The clamp 101 and the infusion circuit clamp 102 are required.

  During dialysis, 101 is open and 102 is closed, preventing entry of arterial blood into the infusion circuit 4, and 101 is closed and 102 is opened when returning blood to prevent outflow of arterial blood to the circuit 2. In particular, it is desirable that the clamp 102 is as close as possible to the coupling point C.

  In this case, two circuits (an infusion circuit 4 leading to the infusion bag 11 and an arterial blood circuit 2 leading to the dialyzer 1) run in parallel immediately after the arterial needle placed in the upper arm, which is troublesome for the patient. Not only that, there is a concern that the circuit may get stuck in something and cause troubles such as the needle coming out.

  On the other hand, it is desirable that the connection point C is Y (or y) type like the connector 103, and that the two circuits are substantially integrated by the binding band 104 until the connection point C is sufficiently separated from the patient bed.

  Further, the binding band 104 is not a single snake-like one as illustrated, but may be attached by attaching independent ring-shaped ones at several locations.

FIG. 1 is an overall schematic diagram of a hemodialysis apparatus according to the present invention. FIG. 2 is a model diagram for explaining the operation of the hemodialysis apparatus according to the present invention. FIG. 3 is a model diagram for explaining the operation of the hemodialysis apparatus according to the present invention. FIG. 4 is a model diagram for explaining the operation of the hemodialysis apparatus according to the present invention. FIG. 5 is a model diagram for explaining the operation of the hemodialysis apparatus according to the present invention. FIG. 6 is an overall schematic diagram illustrating another embodiment of the hemodialysis apparatus according to the present invention.

Explanation of symbols

1: dialyzer 2: arterial blood circuit 3: venous blood circuit 4: infusion infusion circuit 5: retention fluid out-drain circuit 6: dialysate circulation circuit 7: dialysate infusion circuit 11: infusion bag 12: infusion outage detector 13: Infusion clamp 14: Blood pump 15: Arterial blood circuit drip chamber 16: Venous blood circuit drip chamber 17: Drainage clamp 18: Bubble detector 19: Venous blood clamp 20: Equalization chamber 21: Infusion pump 22: Flexible diaphragm 23: Shut-off valve 24: Pressure control valve 101: Arterial blood clamp 102: Infusion clamp 103: Connector 104: Cable tie

Claims (1)

An empty fiber membrane hemodialyzer, an arterial blood circuit connected to the inflow side of the blood circuit so as to circulate inside the hollow fiber membrane of the dialyzer, a venous blood circuit connected to the outflow side, and the arterial blood circuit An infusion circuit connected in the middle, a blood pump installed between the dialyser from the junction of the infusion circuit and the arterial blood circuit, and a retention fluid system branched from the middle of the venous blood circuit Dialysate circulation comprising a drain circuit, a venous blood clamp provided in the middle of the venous blood circuit, and a substantially closed circulation circuit in which the dialysate circulates outside the hollow fiber membrane in the dialyzer A circuit and a dialysate injection circuit for supplying new dialysate from outside the system in the middle of the dialysate circulation circuit, and connecting the upstream end of the arterial blood circuit and the downstream end of the venous blood circuit A circulation circuit is formed and the dialysis A dialysate is injected into the dialysate flow circuit from outside the system through an injection circuit, and the dialysate is allowed to flow from the dialysate side to the blood side via the hollow fiber membrane of the dialyzer. While circulating in the blood circulation circuit, the excess inflow dialysate overflows from the staying fluid system discharge circuit, and after circulating through the blood circulation circuit by a predetermined amount of liquid, Instead of stopping the inflow of dialysate, instead of injecting infusion from the infusion infusion circuit, the staying dialysate in the blood circulation circuit is discharged from the drainage circuit outside the staying fluid system, and the dialysate in the blood circulation circuit is discharged. A hemodialysis apparatus configured to be replaced with an infusion injected from the infusion infusion circuit.

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