JP2503019B2 - Plasma collection device - Google Patents

Description

TECHNICAL FIELD The present invention relates to a plasma collection device for collecting plasma, which is a raw material of a plasma preparation used for treatment and nutritional supplementation in the medical field, from a blood donor by membrane separation, and in particular, The present invention relates to a single needle type device that automatically performs a blood removal and blood return cycle.

(Prior Art) Conventionally, plasma is collected mainly by using a centrifuge, but recently, a plasma collection method using a separation membrane has been studied (Medical Instruments Vol. 54 No. 11, 1984, P534). ~ P539 etc.). Among them, the single needle method, which repeats blood removal and blood return with a single puncture needle, is said to be an excellent method with less mental burden on the donor. In this method, blood is taken out from a blood collecting needle with a pump, separated into a blood cell component and a plasma component with a membrane module, and the separated blood cell component and plasma component are respectively stored in a bag. When a predetermined amount of blood cell components is accumulated in the bag, the blood edge pump is rotated in the opposite direction to return the blood cell components in the bag from the blood collection needle to the donor,
A predetermined amount of plasma component is collected by repeating the above operation (for example, JP-A-60-256466 and JP-A-60-261461).

(Problems to be Solved by the Invention) However, in the above-described single-needle plasma collection method, the physiological saline filled in the blood channel and the membrane module at the end of priming is converted into the plasma bag from the plasma channel at the start of blood removal. There was a problem that the collected plasma was diluted because it was introduced. In addition, during the second and subsequent blood removal, blood cell components with a high hematocrit value that remain in the blood flow path are introduced into the membrane module, which reduces the hypercapacity of the membrane module and makes stable plasma collection difficult. There was a problem.

Therefore, an object of the present invention is to provide a plasma collection device that does not dilute the collected plasma with a priming solution, fully exerts the ability of the membrane module, and can collect plasma stably. It is to be.

(Means for Solving Problems) In order to achieve the above object, the configuration of the present invention is shown in FIG.

The blood channel 1 is a membrane module 3 that separates the blood taken out from the blood collecting needle H into blood cell components and plasma components, a bag 6 that stores the blood cell components separated by the membrane module 3, and a flow rate of the blood channel 1 ( It is equipped with a first detector 5 for detecting the amount of blood removed) and an air detector 15 for detecting the invasion of air into the flow channel, and moreover, it is provided on the downstream side of the membrane module 3 in the blood flow channel 1. A reversible blood pump 4 is provided. Further, the bypass flow passage 17 for bypassing the membrane module is configured so that the flow passage switching means 14 switches between the blood flow passage and the bypass flow passage. The separated blood cell component is stored in the bag 6, and when returning blood, the blood pump 4 is reversed to return the blood cell component in the bag 6 to the human body from the blood collection needle H through the bypass channel.

The plasma channel 2 includes a bag 7 that stores the plasma components separated by the membrane module 3, a plasma pump 8, and a plasma channel 2.
And a second detector 9 for detecting the flow rate of the plasma component, and stores the plasma component separated by the membrane module 3 in the bag 7.

The membrane module 3 has its blood cell component outlet arranged at the top. Although it is usually set in the vertical direction, the blood cell component may be arranged so that the outlet is at the upper part and the outlet for the plasma component is at the lowermost part.

On the other hand, as control means, blood removal starting means 18, blood returning means 19,
A blood removing means 20 and a pump stopping means 21 are provided. The blood removal start means 18 receives a start signal from the outside, operates the flow path switching means 14 to close the bypass flow path 17, drives the blood pump 4 in the normal direction, and supplies blood to the membrane module. Then, the priming liquid in the membrane module is expelled to the bag 6 with blood. When the first detector 5 detects an amount of blood removed so that the priming liquid in the membrane module is expelled by blood, the plasma pump 8 is driven by receiving the detection signal from the detector to start the collection of plasma. . Further blood return means 19
When the blood removal amount reaches the set amount by receiving the detection signal from the first detector 5, the flow passage switching means 14 is operated to form the bypass flow passage 17, and the plasma pump 8 is stopped. ,
The blood pump 4 is reversely driven to return the blood components in the bag 6 through the bypass passage 17. Next, when the air detector 15 detects air by the blood removing means 20, the blood pump 4 is driven in the normal direction in response to the detection signal from the detector 15 to perform blood removal, and blood is filled up to the bypass flow path. When the first detector 5 detects a sufficient blood removal amount, the flow path switching means 14 is operated to close the bypass flow path 17, the plasma pump 8 is driven, and plasma is collected again. Blood return means 19 and blood removal means
20 are operated alternately, and when the pump stop means 21 receives the detection signal from the second detector 9 and the amount of collected plasma reaches a predetermined amount, the driving of the blood pump 4 and the plasma pump 3 is stopped and the plasma is stopped. End the collection of.

(Operation) According to the above configuration, the plasma pump is driven only when the first detector detects the amount of blood removed until the priming liquid in the membrane module is replaced with blood at the start of blood removal. Never want plasma to enter the flow path. When the first detector detects the blood removal amount until the blood cell component filled in the bypass flow path is replaced with blood during the second and subsequent blood removal, the blood flow path is driven in the blood flow path to drive the plasma pump. The residual thick blood cell components are not introduced into the membrane module. Since the priming solution filled in the blood channel and the membrane module is infused to the donor at the time of the first blood return, it is possible to prevent the donor's extracorporeal blood volume from decreasing and reduce the burden on the donor.

(Embodiment) Next, an embodiment of the present invention will be described with reference to the drawings. First, the plasma collection apparatus will be described prior to the description of the plasma collection operation. Figure 2 shows an example of using ACD solution as an anticoagulant.

FIG. 2 is a flow chart at the time of plasma collection (blood removal), where 1 is a blood channel, 2 is a plasma channel, and 17 is a bypass channel. Since the bypass flow path is closed during blood removal, the blood taken out from the blood collection needle H enters the first chamber 31 that detects the blood drawing pressure, and then is boosted by the blood pump 4 to the inlet pressure of the membrane module 3. To the second chamber 23 for detecting, and is introduced from below into the membrane module 3 set in the up-down direction and separated into blood cell components and plasma components.
The membrane module 3 contains a membrane for separating plasma and blood cells, for example, a flat plate-shaped, tube-shaped, or hollow fiber-shaped separation membrane made of polyvinyl alcohol, polysulfone, polyethylene, or the like. Usually, a hollow fiber membrane module in which a large number of hollow fiber-shaped separation membranes are housed in a housing is used.

The blood cell components separated by the membrane module 3 are supplied to the bag 6 that stores blood cells and stored.

Further, the blood inlet of the blood flow channel 1 is connected with a flow channel 26 for supplying an anti-coagulant, which prevents coagulation of the blood to be treated, for example, an ACD solution, to the blood flow channel 1 via an ACD pump 27. The ACD liquid supply channel 26 is connected to the ACD liquid container 24. At the time of blood removal, the ACD solution is supplied from the bag 24 to the blood flow path 1 in a constant amount, and the supply amount is detected by the detector 28.

Further, the first chamber 31 is connected to a sensor 32 for detecting the blood drawing pressure, and when the pressure exceeds a predetermined value, all pumps are stopped. Second Chamba
An inlet pressure sensor 24 to the membrane module is connected to 23. Further, a sensor 25 for detecting the pressure inside the plasma chamber separated by the membrane is connected to the air inlet of the membrane module, and the transmembrane pressure difference (TMP) is detected by the two sensors 24, 25. The plasma extraction speed of the plasma pump 8 is controlled so that the transmembrane pressure difference becomes a predetermined value.

The plasma component separated by the membrane module 3 is the plasma pump 8
Is stored in the bag 7 that stores the plasma.

When returning the blood cell components, the bypass flow path 17 is opened, the plasma pump 8 is stopped, the blood pump 4 is reversed, and the ACD pump 27 is stopped.
The blood cell component inside is returned to the human body from the blood collection needle H through the bypass flow path 17. The bypass flow path 17 and the blood flow path 1 are switched by the flow path switching means 14. A three-way switching valve is usually used as the flow path switching means, but two two-way valves may be used.

An air detector 15 is provided at the outlet of the membrane module 3 of the blood flow path 1 to detect that blood cells in the bag have been returned and blood has entered the blood flow path when returning blood. The detector 15 is usually of a type that emits light or ultrasonic waves from one of the blood channels and measures the transmittance thereof.

The blood pump 4 has a first detector 5 for detecting the flow rate (blood removal amount) of the blood flow path 1 based on the rotation speed of the blood pump, and the plasma pump 8 has the rotation speed of the plasma pump. Second detectors 9 that detect the flow rate of the plasma flow path 2 (the amount of collected blood plasma) are connected to each other.

40 is a control device composed of a micro computer,
During blood processing, the control device 40 observes the flow rate detection signals from the detectors 5 and 9, the air detection signal from the detector 15 and the pressure detection signals from the pressure sensors 32, 24 and 25,
Plasma pump 8 so that the flow rate of blood channel 1 and plasma channel 2 and the transmembrane pressure difference (TMP) of membrane module 3 become appropriate values.
Controls the number of rotations and processes blood while repeating blood removal and blood supply. When the blood drawing pressure becomes abnormal, all pumps are stopped.

Next, the operation of the blood plasma collecting apparatus having the above configuration will be described.

In FIG. 2, the blood collection needle H is connected to the blood donor.
Further, the control device 40 includes a blood pump 4, blood plasma pump 8 that is driven and stopped, and blood removal start means 18, a blood return means 19, a blood removal means 20, and a pump stop means that operate each flow path switching means 17.
21 and 21 are built in.

On the other hand, the inside of the hollow fiber of the membrane module 3 for which priming has been completed, the bypass channel 17 and the blood channel 1 are filled with the priming liquid. The flow path switching means 14 is switched so that the bypass flow path communicates with the bag 6 at the end of priming. This state is shown in step S in FIG.
Shown as -1.

Plasma collection is started from step S-1 in FIG. 3. First, the outline of plasma collection is based on steps S-2 to S-6 in FIGS. 4 to 8 and the flow chart in FIG. Explain.

In FIG. 9, abbreviation symbols are used for the respective parts. The abbreviations are as shown in FIGS. 4 to 8, blood pump 4 is BP, plasma pump 8 is PP, ACD pump 1
9 is represented by ACD P, and the flow path switching means 14 is represented by PV, and PV is closed when the bypass flow path and the bag 6 are communicated with each other.

In step S-2 of FIG. 4, all pumps 5,
8, 19 are stopped, and the flow path switching means 14 is switched so that the bypass flow path and the bag 6 are communicated with each other, the control device 40 operates in response to a start signal from the outside, and the flow path switching means When the ACD pump 27 and the blood pump 4 are driven by activating 14 and closing the bypass flow passage 17, 40-60 ml from the donor
Blood is taken out in minutes. This blood is supplied to the membrane module 3 while mixing the ACD solution. At this time, since blood is supplied into the hollow fiber from the lower side of the membrane module 3, the priming liquid in the hollow fiber is expelled by the blood and introduced into the bag 6 from the module.

When a blood removal amount (for example, 100 ml) enough to expel the priming solution in the membrane module 3 is reached, a detection signal is received from the first detector 5, and the plasma pump is controlled by the controller 40 at step S-3 shown in FIG. Drive 8 at 10-20 ml / min. As a result, the blood cell components separated by the membrane module are stored in the bag 6, and the plasma components are stored in the bag 7.

Further, in response to the detection signal from the first detector 5, when the blood removal amount reaches a predetermined value (250 to 350 ml), the blood removal starting step is considered to be completed, and in step S-4 shown in FIG. By the control device 40, the flow passage switching means 14 is operated to open the bypass flow passage 17, the driving of the plasma pump 8 and the ACD pump 27 is stopped, and the blood pump 4 is reversely driven at 50 to 80 ml / min and returned. Enter the blood process. In this step, the blood cell components and the priming liquid that have been stocked in the bag are returned to the donor through the bypass channel. When the air detection signal from the air detector 15 is received, it is assumed that all the blood cell components in the bag have been taken out of the bag and the return to the donor has been completed, and the control device 40 in step S-5 shown in FIG. Thus, the ACD pump 27 is driven, the blood pump 4 is driven in the normal direction, and the blood removal process starts. Blood is first passed through the bypass channel so that the concentrated blood cell components remaining in the blood channel at the start of the blood removal step are not introduced into the membrane module. At this time, when the blood cell component remaining in the bypass channel reaches the blood removal amount (10 to 30 ml) to be replaced with blood, the detection signal is received from the first detector 5, and the step S- shown in FIG. At 6, the flow path switching means 14 is operated to close the bypass flow path 17, and the plasma pump 8 is driven to collect plasma.

When the plasma component is collected by repeating the cycle of the blood removal step and the blood return step, when the flow rate (plasma collection amount) of the plasma channel 2 reaches a predetermined value upon receiving a detection signal from the second detector 9. Assuming that the plasma collection is completed, the driving of all the pumps 4, 8, 27 is stopped, and the plasma collection is completed.

When the collection of plasma is completed, a blood collection process for returning the blood remaining in the blood channel 1 and the membrane module 3 to the donor is started. In the collecting step, the flow path switching means 14 is operated to close the bypass flow path 17, and the blood pump 4 is reversely driven as in the blood returning step shown in FIG. During this time plasma pump 8 and AC
The D pump 27 remains stopped. When the blood pump 4 is driven in the reverse direction and the blood remaining in the membrane module and the blood flow path is returned to the donor and the first chamber 21 of the blood flow path 1 is emptied, the air detection provided at the outlet of this chamber is detected. The blood pump 4 is stopped in response to the detection signal from the container 13. Next, the valve 11 attached to the opening provided on the upper side wall of the membrane module 3 is opened, and at the same time, the plasma pump 8 is driven to send the residual plasma in the membrane module into the bag 7, and then the plasma pump 8 is stopped. Then, the recovery process is completed.

Using the device of the present invention, the hematoclip value 40
The results of collecting plasma using% bovine blood are shown.

Conditions: Membrane module 0.4 m ² , polysulfone Blood flow rate (ml / min) Blood collection; blood pump 50, plasma pump 20 Returning blood; blood pump 70, plasma pump 0 1 cycle blood collection volume 250 ml, but blood cell component conversion collected plasma volume 400ml Result: Collection time 39 minutes Maximum TMP 55mmHg (TMP = Membrane module inlet pressure-Membrane module overpressure) Total protein concentration of collected plasma 99% (assuming the concentration of the stock solution is 100%) Collected plasma blood coagulation factor ( (VIII, IX) Permeability 98% (Active concentration is 100%) (Effect of the invention) As described above, the device of the present invention allows the membrane module and the blood flow path to flow into the membrane module during the first blood removal. After replacing the remaining priming solution with the blood of the donor, by starting the plasma pump by starting the plasma pump, the influence of dilution by the priming solution can be avoided and high-quality plasma with a high protein concentration can be collected. In addition, at this time, the priming solution stored in the blood cell bag can be infused to the donor at the time of the first blood return to prevent a decrease in the extracorporeal circulating blood volume, thus reducing the burden on the donor.

Furthermore, at the start of the second and subsequent blood collections, after detecting that the blood volume taken out from the blood donor was larger than the filling volume from the blood collection needle to the bypass channel, the plasma pump was started and plasma was collected. By doing so, it is possible to prevent blood with a high hematocrit value remaining in the blood flow path from passing through the membrane module at the end of the blood return, so that the pressure rise in the membrane module is prevented and plasma collection is stable. It can be performed in a short time.

[Brief description of drawings]

FIG. 1 is a flow chart showing the configuration of the present invention, FIG. 2 is a flow chart showing a state during blood collection, and FIGS. 3 to 8 are simplified flow charts showing the operation of the device of the present invention. FIG. 9 is a flow chart showing the control method of the device of the present invention. 1 ... Blood flow path, 2 ... Plasma flow path 3 ... Membrane module, 4 ... Blood pump 5 ... First detector, 6 ... Blood cell storage bag 7 ... Plasma storage bag, 8 ... Plasma Pump 9 …… Second detector, 15 …… Air detector 17 …… Bypass flow path, 18 …… Blood removal starting means 19 …… Blood returning means, 20 …… Blood removing means 21 …… Pump stopping means, H ... Blood collection needle

Claims (1)

(57) [Claims] 1. A blood channel 1 for introducing blood from a blood collecting needle H into a membrane module 3 to separate it into blood cell components and plasma components, and storing the separated blood cell components in a bag 6, and the membrane module. Plasma flow channel 2 for storing the separated plasma components in bag 7, and bypass flow channel 17 for bypassing the membrane module.
A forward and reverse blood pump 4 provided on the downstream side of the membrane module 3 of the blood channel 1, a plasma pump 8 provided on the plasma channel 2, the blood channel 1 and a bypass channel A flow path switching means 14 for switching the flow path 17, a first detector 5 for detecting the flow rate of the blood flow path, and a second detector 5 for detecting the flow rate of the plasma flow path.
Detector 9, an air detector 15 provided at the bag outlet of the blood flow path, and a start signal from the outside to operate the flow path switching means 14 to close the bypass flow path 17, Blood removal that drives the blood pump 4 in the normal direction to introduce blood into the membrane module 3 and drives the plasma pump 8 when the blood is filled up to the membrane module in response to the detection signal from the first detector 5. Upon receiving a detection signal from the starting means 18 and the first detector 5, when the blood removal amount reaches a set amount, the flow path switching means 14 is operated to form the bypass flow path 17, and The plasma pump 8 is stopped, the blood pump 4 is driven in reverse, and the blood returning means 19 for returning the blood cell components in the bag 6 to the human body through the bypass flow path 17 and the air detection signal from the air detector 15 are received. Drive the blood pump 4 in the normal direction, and detect the detection signal from the first detector 5. Only in when the blood has been filled to the bypass passage, and closing the bypass passage 17 by operating the flow path shifting unit 14, blood removal means 20 for driving the plasma pump 8
When the blood returning means 19 and the blood removing means 20 are alternately operated and a predetermined amount of plasma is collected, the blood pump 4 and the plasma pump 8 receive the detection signal from the second detector 9. A plasma collection apparatus comprising pump stopping means (21) for stopping.