JP2001170165A - Blood component collector - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide a blood component collector that can collect platelets efficiently and can obtain a high density liquid containing platelets. SOLUTION: The blood component collector 1 is a device for a blood component collecting circuit 2 provided with a rotor 142 having a blood storage space, a centrifugal separator 20 centrifugally separating the blood by the rotation of the rotor 142, the first line 21 connecting a blood drawing needle 29 and the inlet of the centrifugal separator 20, the second line 22 connected to the centrifugal separator 20, the third line 23 to inject an anticoagulant, the first tube 25a connected to the first line 21 and a plasma collection bag 25 connected to the second line 22, and a platelet collecting bag 26 connected to the second line 22. The blood content collector 1 is provided with a control section to control the number of centrifugal revolution of the rotor of the centrifugal separator, considering the speed of a blood stream of a blood donor at the time of collection.

Description

DETAILED DESCRIPTION OF THE INVENTION

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to a blood component collecting apparatus for separating a predetermined blood component from blood.

[0002]

2. Description of the Related Art At the time of blood collection, at present, blood is separated into various blood components by centrifugation or the like for reasons such as effective use of blood and reduction of the burden on donors, and only components necessary for the transfuser are collected. Blood is collected from components collected and returned to donors. In such a component blood sampling, when a platelet preparation is obtained, blood collected from a donor is introduced into a blood component collection circuit, and a plasma, a centrifugal bowl called a centrifugal bowl installed in the blood component collection circuit is used.
The blood is separated into four components, white blood cells, platelets, and red blood cells, and the platelets are collected in a container to produce a platelet product, and the remaining plasma, white blood cells, and red blood cells are returned to the donor.

As a method for collecting platelets, for example, Japanese Patent Application Laid-Open
There is a method disclosed in JP-A-509403. Japanese Patent Publication No. Hei 8-509403 discloses a first method in which a liquid is added to whole blood at a predetermined flow rate and diluted and sent to a centrifugal bowl. Whole blood is sent to a centrifugal bowl, and centrifuged to separate low-density components. After separating the medium density component and the high density component into the first container and taking out the low density component into the first container, the circuit is switched and the low density component is circulated at the first flow rate (constant speed) so as to be circulated in the centrifugal bowl. A second method is disclosed in which a density component region is expanded and a medium density component is extracted while recirculating at a second flow rate (acceleration).

[0004]

The number of centrifugal rotations is constant irrespective of the blood donor, and when the blood flow rate at the time of blood collection is small, the blood collection time becomes longer in relation to the increase in the amount of blood removed, and the inside of the centrifuge bowl becomes longer. In some cases, the concentration of blood cell components was further advanced (high concentration), and platelet collection sometimes did not function well. Therefore, an object of the present invention is to provide a blood component collection device that has a high platelet collection efficiency and can obtain a high-concentration platelet-containing liquid.

[0005]

Means for achieving the above object include a rotor having a blood storage space therein, an inlet and an outlet communicating with the blood storage space, and rotating the rotor to rotate the inlet. A centrifugal separator for centrifuging the introduced blood in the blood storage space, a first line for connecting a blood collection needle or a blood collection device connection to an inlet of the centrifuge, and the centrifuge. A second line connected to the outlet, a third line connected to the first line for anticoagulant injection, and a first tube connected in the middle of the first line A blood component collection device comprising a blood component collection circuit comprising a plasma collection bag having a second tube connected to the second line and a platelet collection bag connected to the second line, The blood Min draw device, the blood flow velocity during blood donors, it is to have the blood component collection apparatus comprising a control unit having a function of changing a centrifugal rotation speed of the rotor of the centrifuge. Preferably, the control unit has a function of changing a centrifugal rotation speed of a rotor of the centrifugal separator according to a blood component concentration of the blood donor and a blood flow speed at the time of blood collection of the blood donor. Further, the blood component concentration of the donor may be a hematocrit value.

[0006] The blood component collecting apparatus may further include a centrifugal separator driving device for rotating the rotor of the centrifugal separator, and a centrifugal separator side with respect to a connection between the first line and the first tube. A first liquid supply pump for the first line, a second liquid supply pump for the third line, and a circuit for opening and closing the flow path of the blood component collection circuit. A plurality of flow path opening / closing means, a control unit for controlling the centrifugal separator driving device, the first liquid feeding pump, the second liquid feeding pump, and the plurality of flow path opening / closing means, The control unit is configured to collect the blood to which the anticoagulant is added, to separate the collected blood and to collect the separated plasma in the plasma collection bag, and to collect the plasma collected in the plasma collection step. Plasma in the plasma collection bag At least one plasma collection / circulation step consisting of a plasma circulation step for circulating in the centrifuge, and after the plasma collection / circulation step, by accelerating the plasma circulation speed by the first liquid feeding pump, A platelet collection step of allowing platelets to flow out of the centrifuge and collecting platelets in the platelet collection bag is performed,
After the completion of the platelet collection step, the centrifuge drive device, the first liquid feed pump, and the blood pump are operated so as to perform a platelet collection operation for performing a blood return step of returning blood in the centrifuge. It is preferable to control the second liquid feed pump and the plurality of flow path opening / closing means.

[0007] Then, after the plasma collection / circulation step is completed, the control unit controls the first liquid supply pump and the second liquid supply pump before accelerating the plasma circulation speed by the first liquid supply pump. Operating the liquid feeding pump to collect blood to which the anticoagulant has been added, and operating the centrifugal separator driving device to collect a predetermined amount of plasma from the blood into the plasma collection bag. It is preferred that this be done. The control unit controls the plasma collection / circulation step to be performed twice. In the first plasma collection / circulation step, the plasma in the plasma collection bag is supplied to the centrifugal separator at a constant speed. Plasma collection to be circulated at
A constant-speed circulation step is performed, and in the second plasma collection / circulation step, control is performed such that a plasma collection / accelerated circulation step of circulating plasma in the plasma collection bag while accelerating the plasma in the centrifuge is performed. It is preferable that Further, the blood component collection circuit includes a buffy coat collection bag connected to the second line, the control unit is after the platelet collection step,
Before the blood return step, it is preferable to perform a buffy coat collecting step of causing a buffy coat to flow out of the centrifuge and collecting the buffy coat in the buffy coat collecting bag.

[0008] Further, when the platelet collection operation is further performed after the completion of the buffy coat collection step, the control unit transmits the collected buffy coat to the next plasma collection / collection step.
It is preferable that the first liquid feed pump and the plurality of flow path opening / closing means are controlled so that a buffy coat return step of returning the buffy coat to the inside of the centrifuge is performed before the circulation step. The blood component collection device includes a centrifugal separator driving device for rotating the rotor of the centrifugal separator, and the control unit stores a minimum rotor rotation number storage function and a blood component concentration of the donor. A rotor rotation speed calculation function for calculating a rotor rotation speed in consideration of the blood flow speed at the time of blood collection by the donor, wherein the rotor rotation speed calculated by the rotor rotation speed calculation function is the minimum rotor rotation speed. If the calculated rotor speed is smaller than the minimum rotor speed, the centrifuge drive device is controlled to rotate the rotor at the calculated rotor speed. Preferably, it has the function of controlling the centrifuge drive to rotate the rotor by a number.

The blood component collecting apparatus has a centrifugal separator driving device for rotating the rotor of the centrifugal separator, and a hematocrit value input section or a hematocrit value measuring function. , A blood flow velocity calculation function at the time of blood collection of the blood donor, and a minimum rotor rotation number storage function, and the blood flow velocity calculated by the blood flow velocity calculation function is a constant value. If it is larger, the rotor rotation speed calculation function calculates the rotor rotation speed suitable for the hematocrit value using the input or measured hematocrit value, and calculates the blood flow velocity calculated by the blood flow velocity calculation function. Is smaller than or equal to a certain value, the rotor speed calculation function calculates the hematocrit calculated using the input or measured hematocrit value. The rotor speed calculated by a predetermined value lower than the rotor speed suitable for the rotor speed is calculated, and if the rotor speed calculated by the rotor speed calculation function is larger than the minimum rotor speed, the calculated rotor speed is calculated. The centrifugal separator driving device is controlled to rotate the rotor at the rotation speed, and if the calculated rotor rotation speed is smaller than the minimum rotor rotation speed, the centrifugal separator is rotated to rotate the rotor at the minimum rotor rotation speed. It is preferable to have a function of controlling the separator driving device. And
The hematocrit value measurement function may be a hematocrit value measurement sensor provided at a position closer to the blood collection needle than the connection with the third line for injecting an anticoagulant, which is the first line. Good. Further, the hematocrit value measurement function may be a hematocrit value measurement function using a centrifuge at the time of the first plasma collection step.

[0010]

DESCRIPTION OF THE PREFERRED EMBODIMENTS A blood component collecting apparatus according to the present invention will be described with reference to an embodiment shown in the drawings. FIG. 1 is a plan view showing a configuration example of a blood component collection circuit used in the blood component collection device of the present invention. FIG. 2 is a plan view of a cassette housing portion of the blood component collection circuit of FIG. FIG. 3 is a partially cutaway sectional view showing a state in which a driving device is mounted on a centrifuge used in a blood component collection circuit, and FIG. It is a conceptual diagram of one Example of an apparatus. The blood component collecting apparatus 1 of the present invention has a rotor 142 having a blood storage space therein, an inlet 143 and an outlet 144 communicating with the blood storage space, and blood introduced from the inlet 143 by rotation of the rotor 142. 20 for centrifuging blood in a blood storage space
A first line 21 for connecting a connection part to the blood collection needle 29 or the blood pool to an inlet 143 of the centrifuge 20, and a second line connected to an outlet 144 of the centrifuge 20 22, a third line 23 connected to the first line 21 for anticoagulant injection, and a first line 25a connected to the first line 25 and the second line 22 connected to the first line 21. This is a blood component collection device for the blood component collection circuit 2 including a plasma collection bag 25 having two tubes 25b and a platelet collection bag 26 connected to the second line 22.

The blood component collection device 1 includes a centrifuge drive device 10 for rotating the rotor 142 of the centrifuge 20 and a first liquid supply pump 1 for the first line 21.
1 and the second pump 12 for the third line 23
And a plurality of flow path opening / closing means 81, 82, 83, 84, 85, 86, for opening and closing the flow path of the blood component collection circuit 2.
87, the centrifuge drive device 10, the first liquid feed pump 1
A control unit 13 for controlling the first and second liquid feed pumps 12 and a plurality of flow path opening / closing means is provided. Since this blood component collection device is constituted by two pumps, the size of the device can be reduced.

The blood component collecting circuit 2 will be described first. The blood component collection circuit 2 is a circuit for collecting blood components, especially platelets. The platelet collection circuit 2 includes a blood collection device such as a blood collection needle 29, a connection portion to a blood collection device having a blood collection needle or a blood pool connection portion (blood collection device connection portion), a blood collection needle 29 or a blood collection device connection portion, and a centrifuge. 20, a first line 21 (blood collection and blood return line) including a first pump tube 21g, an outlet 144 of the centrifuge 20, and a first line 21.
A second line 22 for connecting the first line 21 to the blood collection needle 29 of the first line 21 and a third line 23 provided with a second pump tube 23a (an anticoagulant injection line). The first tube 25a and the second line 22 connected to the branch connector 21f located on the blood collection needle side of the pump tube 21g of the first line 21.
Collection bag 25 having a second tube 25b connected to the third tube 2 connected to the second line 22
Platelet collection bag 26 with 6a, second line 22
And a fourth line 24 for injecting a liquid (saline) connected to the second line 22. The blood component collection circuit 2 is not a blood collection needle, but a connection unit for connecting to a blood pool such as a blood bag (for example,
(A metal or synthetic resin needle).

As the blood collection needle 29, a known metal needle is used. The first line 21 is connected to the blood collection needle side first line 21 a to which the blood collection needle 29 is connected and the inflow port 14 of the centrifuge 20.
3 and the first line 21b connected to the centrifugal separator. The first line 21a on the blood collection needle side is formed by connecting a plurality of soft resin tubes. The blood collection needle side first line 21a includes a branch connector 21c for connection to the third line 23, a chamber 21d for removing bubbles and microaggregates, and a second line 22 from the blood collection needle side.
Branch connector 21e for connection with the plasma collection bag 25
Branch connector 21f for connection with the first tube 25a
Is provided. An air-permeable and bacteria-impermeable filter 21i is connected to the chamber 21d. The centrifuge-side first line 21b is connected to a branch connector 21f for connection to the first tube 25a, and has a pump tube 21g formed in the vicinity thereof.

A second line 22 connecting the outlet 144 of the centrifuge 20 and the first line 21 has one end connected to the outlet 144 of the centrifuge 20 and the other end connected to the first line 21. Is connected to the connection branch connector 21e. The second line 22 is a branch connector 22a for connection with the second tube 25b of the plasma collection bag 25 and the third tube 26a of the platelet collection bag 26, and a connection branch for connection with the fourth line 24 from the centrifuge side. The baffle coat collecting bag 27 includes a connector 22b, a branch connector 22c for connection to a tube including a bubble removal filter 22f, and a branch connector 22d for connection to a fourth tube 27a of the buffy coat collection bag 27.

One end of the third line 23 is connected to a connection branch connector 21c provided on the first line 21. The third line 23 is connected to the pump tube 23a and the foreign matter removing filter 23 from the connector 21c side.
b, a bubble removing chamber 23c, and an anticoagulant container connecting needle 23d. One end of the fourth line 24 is connected to the connection branch connector 22 b of the second line 22. The fourth line 24 includes a foreign matter removing filter 24a and a saline container connecting needle 24b from the connector 22b side. The plasma collection bag 25 is
A first tube 25a connected to a branch connector 21f located closer to the blood collection needle than the pump tube 21g of the line 21 and a second tube 25b connected to a branch connector 22a of the second line 22. The platelet collection bag 26 includes a third tube 26a connected to the branch connector 22a of the second line 22. The buffy coat collection bag 27 includes a fourth tube 27a connected to the branch connector 22d of the second line 22.

The above-described first to fourth lines 21, 22
The constituent materials of the tube used for forming 2, 23, 24, the pump tube, and the tube connected to the bag include, for example, polyvinyl chloride, polyethylene, polypropylene, polyester such as PET or PBT, ethylene. -Vinyl acetate copolymer, polyurethane,
Examples thereof include thermoplastic elastomers such as polyester elastomers and styrene-butadiene-styrene copolymers. Among them, polyvinyl chloride is particularly preferable. If each tube is made of polyvinyl chloride, sufficient flexibility,
Because flexibility is obtained, it is easy to handle, and it is also suitable for clogging by cleansing or the like. Also, as the constituent material of the branch connector described above, the same material as the constituent material of the tube can be used. As the pump tube, a tube having such a strength as not to be damaged even when pressed by a roller pump is used.

Plasma collection bag 25, platelet collection bag 2
6. The buffy coat collection bag 27 is formed by laminating a resin-made flexible sheet material and fusing (thermal fusion, high-frequency fusion, or the like) or bonding the periphery thereof to form a bag. used. As a material used for each of the bags 25, 26, 27, for example, soft polyvinyl chloride is preferably used. As a plasticizer in the soft polyvinyl chloride, for example, di (ethylhexyl) phthalate (D
EHP), di- (n-decyl) phthalate (DnDP)
Etc. are used. Incidentally, the content of such a plasticizer,
The amount is preferably about 30 to 70 parts by weight based on 100 parts by weight of polyvinyl chloride.

Further, as the sheet material of each of the bags 25, 26, and 27, a polyolefin, that is, a polymer obtained by polymerizing or copolymerizing an olefin such as ethylene, propylene, butadiene, or isoprene, or a diolefin may be used. Specifically, for example, polyethylene,
Polypropylene, ethylene-vinyl acetate copolymer (EV
A), a polymer blend of EVA and various thermoplastic elastomers, or a combination thereof arbitrarily. Furthermore, polyethylene terephthalate (PET), polybutylene terephthalate (PB)
T), polyesters such as poly-1,4-cyclohexanedimethylterephthalate (PCHT), and polyvinylidene chloride can also be used. As the sheet material used for the platelet collection bag 26, it is more preferable to use a sheet material having excellent gas permeability in order to improve the platelet preservability. As such a sheet material, for example,
The above-mentioned polyolefin, DnDP plasticized polyvinyl chloride, or the like is used. Also, without using such a material, a sheet material of the above-described material is used, and the thickness is relatively small (for example, 0.1 to 0.1). About 0.5mm, especially
(Approximately 0.1 to 0.3 mm) is preferable. The platelet collection bag includes, for example, physiological saline, GA
A platelet preservative such as C, PAS, PSM-1 may be pre-filled.

The main part of the blood component collecting circuit 2 is of a cassette type as shown in FIG. The blood component collection circuit 2 includes all lines (first line, second line, third line, and fourth line) and all tubes (first tube, second tube, third tube, and fourth line). Tubes) are partially housed and partially hold them, in other words comprise a cassette housing 28 in which they are partially fixed. Both ends of a first pump tube 21g and both ends of a second pump tube 23a are fixed to the cassette housing 28. The pump tubes 21g and 23a are formed into a loop shape corresponding to the shape of the roller pump by the cassette housing 28. It is protruding. Therefore, the first and second pump tubes 21g and 23a can be easily mounted on the roller pump.

Further, the cassette housing 28 has a plurality of openings located in the cassette housing 28. Specifically, the first opening 91 exposing the first line 21 on the blood collection needle side from the pump tube 21g and allowing the first flow path opening / closing means 81 of the blood component collection device 1 to enter, First tube 25a of plasma collection bag 25
And the second opening 92 through which the second channel opening / closing means 82 of the blood component collection device 1 can enter, and the second tube 25b of the plasma collection bag 25 are exposed. The third in which the third channel opening / closing means 83 can enter.
Opening 93, third tube 2 of platelet collection bag 26
The connection between the fourth opening 94, the second line 22, and the fourth tube 27 a of the buffy coat collection bag 27, which exposes 6 a and allows the fourth flow path opening / closing means 84 of the blood component collection device 1 to enter. Exposing the second line 22 located on the centrifugal separator side (upstream side) of the blood sample collection device 1
The fifth opening 95 through which the fifth flow path opening / closing means 85 can enter, between the connection portion with the first line 21 and the connection portion with the fourth tube 27a of the buffy coat collection bag 27 (the The sixth opening that exposes the second line 22 (downstream from the connection between the second line 22 and the fourth tube 27a) and allows the sixth flow path opening / closing means 86 of the blood component collection device 1 to enter. The portion 96 is provided with a seventh opening 97 that exposes the fourth line 24 and allows the seventh flow path opening / closing means 87 of the blood component collection device 1 to enter.

On the inner surface of the cassette housing 28, the above-mentioned branch connector is fixed. Further, near the side surface of the cassette housing 28, a line and a tube protruding from the side surface of the housing are held,
Further, a reinforcing tube for preventing bending at the housing portion is provided. Cassette housing 28
Is a box-shaped body in which the portion shown by the broken line in FIG. 2 can be stored. Then, the cassette housing 28
Is formed of a synthetic resin having a certain degree of rigidity. The blood component collection device 1 includes the cassette housing mounting portion (not shown). For this reason, by mounting the cassette housing 28 on the cassette housing mounting portion of the blood component collecting apparatus 1, each line and each tube of the portion exposed from the opening of the cassette housing 28 automatically correspond to the corresponding channel opening / closing means. Attached to.
Thus, the circuit can be easily mounted, and the preparation for collecting blood components can be quickly performed. In addition, the blood component collection device 1 is provided with two pumps near the cassette housing mounting portion. For this reason, the cassette housing 28
It is easy to attach the pump tube, which is more exposed, to the pump.

The centrifuge 20 provided in the blood component collection circuit 2 is usually called a centrifuge bowl, and separates blood components by centrifugal force. As shown in FIG. 3, the centrifugal separator 20 has a vertically extending tube 141 having an inlet 143 formed at an upper end thereof, and rotates around the tube 141, and is liquid-tightly sealed to the upper portion 145. Hollow rotor 14
And 2. A flow path (blood storage space) is formed in the rotor 142 along the bottom and the inner surface of the peripheral wall,
An outlet 144 is formed so as to communicate with an upper part of the flow path. In this case, the volume of the rotor 142 is, for example, about 100 to 350 ml.

The rotor 142 is rotated under predetermined centrifugal conditions (rotation speed and rotation time) set by the rotor rotation driving device 10 provided in the blood component collection device 1. According to the centrifugation conditions, a blood separation pattern in the rotor 142 (for example, the number of blood components to be separated) can be set. In the present embodiment, as shown in FIG.
31, centrifugal conditions are set so as to be separated into the buffy coat layer 132 and the red blood cell layer 133.

Next, the blood component collecting apparatus 1 of the present invention shown in FIG. 4 will be described. The blood component collection device 1 includes a centrifuge drive device 10 for rotating the rotor 142 of the centrifuge 20, a first liquid feed pump 11 for the first line 21, and a third line 23. And a plurality of flow passage opening / closing means 81, 82, 83, 84, 8 for opening and closing the flow passage of the blood component collection circuit 2.
5, 86, 87, and a control unit 13 for controlling the centrifuge drive device 10, the first liquid feed pump 11, the second liquid feed pump 12, and the plurality of flow path opening / closing means. Further, the blood component collection device 1 is attached above the turbidity sensor 14 and the centrifuge 20 which are attached to the second line 22 on the centrifugal separator side (upstream side) from the connection portion 22a with the second tube 25b. And a weight sensor 16 for detecting the weight of the plasma collection bag 25.

In this embodiment, the blood component sampling device has a hematocrit value input unit. The control unit 13 includes two pump controllers (not shown) for the first liquid supply pump 11 and the second liquid supply pump 12, and includes a control mechanism of the control unit 13 and the first liquid supply pump 11 and The second liquid feed pump 12 is electrically connected via a pump controller, and is also electrically connected to a drive controller included in the centrifuge drive device (rotor drive device) 10. The control unit 13 has a function of changing the number of centrifugal rotations of the rotor of the centrifuge according to the blood flow speed at the time of blood collection by the blood donor. In particular, in the blood component collection device of this embodiment, the centrifugal rotation speed of the rotor of the centrifuge is changed according to the blood component concentration (specifically, hematocrit value) of the donor and the blood flow speed at the time of blood collection of the donor. It has the function to do. The blood component concentration of the donor may be, for example, a hematocrit value, an expected number of collected platelets calculated from the hematocrit value and the platelet concentration, a platelet concentration, and further, an average red blood cell volume, sex, height, and body weight.

The control unit 13 has a minimum rotor rotation speed storage function and a rotor rotation speed calculation for calculating the rotor rotation speed using the blood component concentration of the blood donor and taking into account the blood flow speed at the time of blood collection of the blood donor. If the rotor speed calculated by the rotor speed calculation function is greater than the minimum rotor speed, the centrifuge drive device is controlled to rotate the rotor at the calculated rotor speed. When the calculated rotor rotation speed is smaller than the minimum rotor rotation speed, a function of controlling the centrifugal separator driving device to rotate the rotor at the minimum rotor rotation speed is provided. Specifically, the blood component collection device includes a centrifuge driving device for rotating the rotor of the centrifuge and a hematocrit value input unit or a hematocrit value measurement function, and the control unit calculates the rotor rotation speed. Rotor speed calculation function, a blood flow speed calculation function at the time of blood collection of a blood donor, and a minimum rotor speed storage function, when the blood flow speed calculated by the blood flow speed calculation function is larger than a certain value. The rotor rotation speed calculation function calculates the rotor rotation speed suitable for the hematocrit value using the input or measured hematocrit value, and when the blood flow velocity calculated by the blood flow velocity calculation function is equal to or less than a certain value, , The rotor speed calculation function uses a hematocrit value that is calculated using the input or measured hematocrit value. A centrifuge that calculates a lower fixed rotation speed and if the calculated rotation speed of the rotor is higher than the minimum rotation speed by the rotor rotation speed calculation function, rotates the rotor at the calculated rotation speed. It has a function of controlling the driving device and controlling the centrifugal separator driving device to rotate the rotor at the minimum rotor speed when the calculated rotor speed is smaller than the minimum rotor speed.

More specifically, the control unit 13 includes, as rotor speed calculating functions, a hematocrit value and a proper relationship data storage unit for the rotor speed, a blood flow speed calculating function at the time of blood collection by a donor, and an input function. Alternatively, it is provided with a function of calculating an appropriate rotor speed from a measured hematocrit value described later and stored data of a proper relational expression between the hematocrit value and the rotor speed. The appropriate relational data between the hematocrit value and the rotor speed are data obtained by actually collecting platelets at various rotor speeds using blood with a large hematocrit value and obtaining good results (hematocrit value and rotor speed). ) Can be calculated. The relational expression can be expressed as a first-order, second-order, or even higher-order regression equation. An example of the proper relational expression data of the hematocrit value (x:%) and the rotor rotation speed (y: rpm) obtained by the present inventors is as follows.

[0028] ^{y = 40x + 3000 y = -0.94505x} 2 + 110.18x + 1744 y = 0.0667x 3 -8.7619x 2 +391.9
x-1277.4

In any of these examples of appropriate relational expression data, the tendency is that the lower the hematocrit value, the lower the proper rotor speed, and conversely, the higher the hematocrit value, the higher the proper rotor speed. Then, when the hematocrit value (x) is input, an appropriate rotor speed (y) is calculated from the stored appropriate relational data between the hematocrit value and the rotor speed. The centrifugal separator driving device is configured to rotate the rotor at the rotor rotation speed calculated by the rotor rotation speed calculation function when necessary (during a later-described plasma collection / circulation step or second plasma collection / circulation step). Control.

Thus, in response to the hematocrit value,
By changing the rotor speed, for example, in the case of a blood donor having a low hematocrit value, it is possible to prevent an excessive compression phenomenon of a separated blood component layer due to excessive centrifugation called packing. When such packing occurs, the platelet layer is also compressed, so that platelet collection is difficult and collection efficiency is reduced. Conversely, in the case of a blood donor having a high hematocrit value, it is possible to prevent a state of insufficient separation due to insufficient centrifugation. When such an insufficiently separated state occurs, many platelets not located in the platelet layer are present in the blood cell layer or plasma, and the collection efficiency is reduced. However, in the apparatus of the present invention, the occurrence of the above-described packing phenomenon and insufficient separation is extremely reduced, and efficient platelet collection can be performed.

Further, the control unit 13 has a function of changing the centrifugal rotation speed of the rotor of the centrifuge according to the blood flow speed at the time of blood collection by the donor. In particular, in the blood component collection device of this embodiment, the centrifugal rotation speed of the rotor of the centrifuge is changed according to the blood component concentration (specifically, hematocrit value) of the donor and the blood flow speed at the time of blood collection of the donor. It has the function to do. Specifically, it corrects the rotor rotation speed calculated using the above hematocrit value.

The control unit 13 stores the following equation (1). V _DAVE = BPV ÷ (T1−T2) (Equation 1, blood flow velocity calculation equation) Equation 1 is used to calculate the average blood collection speed during the blood collection operation. T2: Total time during which circulation operation is performed and blood collection is stopped BPV: Total amount of blood processed (collected) in that cycle Average blood collection speed: V _DAVE

If the average blood collection speed V _DAVE calculated by the blood flow velocity calculation function is a low flow rate equal to or less than a certain flow rate (specifically, 40 ml / min or less),
The rotor speed is calculated by the following equation. N (corrected rotor speed) = Y−D and N (corrected rotor speed) ≧ 4400 D is an arbitrary fixed value (predetermined value), and is preferably 100 to 800, for example, 400. That is, when the average blood collection speed: V _DAVE is equal to or less than a certain flow rate, 4400
As long as the rotation speed is equal to or greater than rpm, a value obtained by subtracting a predetermined value (400 rpm) from the normal operation value is output as an adjusted rotor rotation speed, thereby rotating the rotor.

The blood flow velocity is not based on the above-described calculation, but is a sensor (for example, an electromagnetic type) for measuring the blood flow velocity flowing through the blood component collection circuit (for example, the first line 21). A flow meter) may be provided for actual measurement. In this case, from the middle of the first plasma collection step, if the actually measured blood flow velocity is equal to or lower than the predetermined value, the rotation speed of the rotor is calculated again, and the rotation speed of the rotor is calculated based on the calculated corrected rotation speed. The rotation may be controlled.

In the above description, when the blood flow rate is low, the predetermined value (400 rpm) is reduced from the normal calculation value. However, the calculated blood flow rate is not a predetermined value (fixed value). May be changed by the following.
An arithmetic expression in such a case may be N = y− (1 / V _DAVE ) × E and N (corrected rotor speed) ≧ 4400. E is an arbitrary fixed value, 4000 to 3
2000 is preferred, for example 16000.

Further, the control unit is not limited to the one which once calculates y (rotor rotation speed) and calculates the corrected rotor rotation speed N by using it as described above. Average blood collection rate calculated by:
V _DAVE is below a certain flow rate (specifically, 40 ml / m
(in) or less, and may store any one of the following low flow rate rotor rotation speed arithmetic expressions used when the flow rate is low. y = 40x + 3000−D and y ≧ 4400 y = −0.94505x ² + 11.18x + 1744
-D and ^{y ≧ 44 00y = 0.0667x 3 -8.7619x} 2 +39
1.9x-1277.4-D and y ≧ 4400

The channel opening / closing means 81, 82, 83, 8
4, 85, 86, 87 are all connected to the control unit, and their opening and closing are controlled by the control unit 13. Further, a turbidity sensor 14, an optical sensor 15 mounted above the centrifuge 20, and a weight sensor 16 for detecting the weight of the plasma collection bag 25 are also electrically connected to the control unit 13, and The output signal is input to the control unit 13. The control unit 13 has a control mechanism composed of, for example, a microcomputer and a rotor rotation speed calculation function, and includes the weight sensor 16, the optical sensor 15,
The detection signal from the turbidity sensor 14 is input to the control unit 13 as needed. The control unit 13 controls the rotation, stop, and rotation direction (forward / reverse) of each pump based on signals from the turbidity sensor 14, the optical sensor 15, and the weight sensor 16 and, if necessary, controls each flow. The opening / closing of the road opening / closing means and the operation of the centrifugal separator rotation drive device 10 (rotation of the rotor) are controlled.

The first channel opening / closing means 81 is provided for opening / closing the first line 21 on the blood collection needle side from the pump tube 21g. Second channel opening / closing means 82
Is provided for opening and closing the first tube 25a of the plasma collection bag 25. The third channel opening / closing means 83
It is provided to open and close the second tube 25b of the plasma collection bag 25. The fourth channel opening / closing means 84 is provided for opening / closing the third tube 26 a of the platelet collection bag 26. The fifth flow path opening / closing means 85 is connected to the second line 22 at a position closer to the centrifugal separator (upstream side) than the connection 22 d between the second line 22 and the fourth tube 27 a of the buffy coat collection bag 27. It is provided for opening and closing. The sixth flow path opening / closing means 86 is provided between the connection portion 21e with the first line 21 and the connection portion with the fourth tube 27a (downstream from the connection portion between the second line 22 and the fourth tube 27a). ) Is provided to open and close the second line 22. Seventh channel opening / closing means 87
Is provided for opening and closing the fourth line 24. The channel opening / closing means includes a line or tube insertion portion, and the insertion portion has a clamp operated by a drive source such as a solenoid, an electric motor, and a cylinder (hydraulic or pneumatic). Specifically, a pneumatic cylinder clamp operated by pneumatic pressure is suitable. The clamp of the passage opening / closing means operates based on a signal from the control unit 13.

As shown in FIG. 3, the rotor driving device 10 holds a rotor rotation driving device housing 151 for accommodating the centrifuge 20, a leg 152, a motor 153 as a driving source, and the centrifuge 20. Disc-shaped fixed base 1
55. The housing 151 includes the leg 1
It is placed and fixed on the upper part of the reference numeral 52. Further, a spacer 15 is provided on the lower surface of the housing 151 by using a bolt 156.
7, a motor 153 is fixed. Motor 15
A fixed base 155 is fitted to the tip of the third rotating shaft 154 so as to rotate coaxially and integrally with the rotating shaft 154, and the bottom of the rotor 142 is fitted to the upper part of the fixed base 155. A recess is formed. In addition, centrifuge 2
0 is fixed to the housing 151 by a fixing member (not shown). Rotor rotation drive 10
Then, when the motor 153 is driven, the fixed base 155 and the rotor 142 fixed thereto are rotated, for example, at a rotation speed of three.
Spin at 000-6000 rpm.

Further, the rotor rotation driving device housing 1
On the inner wall of 51, the interface of the separated blood components in the centrifuge (for example, plasma layer 131 and buffy coat layer 132)
B, buffy coat layer 132 and erythrocyte layer 133
Optical sensor 15 for optically detecting the position of
Are installed and fixed by a mounting member 158. As the optical sensor 15, an optical sensor that can scan vertically along the outer peripheral surface of the centrifuge 20 is used. This sensor includes a light source that irradiates light toward the shoulder portion of the centrifuge 20 and a light receiving unit that receives light reflected from the centrifuge bowl and returned. That is, LE
A light-emitting element such as D or a laser and a light-receiving element are arranged in a row, and light reflected by a blood component of light emitted from the light-emitting element is received by the light-receiving element, and the received light amount is photoelectrically converted. Have been. Since the intensity of the reflected light differs depending on the separated blood components (for example, the plasma layer 131 and the buffy coat layer 132), the position corresponding to the light receiving element where the received light amount has changed is detected as the position of the interface B.
More specifically, the amount of light received by the light receiving unit when the light passing through the centrifuge 20 is filled with a transparent liquid (plasma or water) and when the light is filled with a buffy coat layer It is detected from the difference that the buffy coat layer has reached the light passing portion. The position at which the buffy coat layer is detected is adjusted by changing the position at which light passes through the inside of the bowl. Usually, once the light beam passing position is determined, it is fixed there.

The turbidity sensor 14 is for detecting the turbidity of the fluid flowing in the second line 22, and outputs a voltage value corresponding to the turbidity. Specifically, a low voltage value is output when the turbidity is high, and a high voltage value is output when the turbidity is low. The first liquid supply pump 11 to which the pump tube 21g of the first line 21 is attached and the second liquid supply pump 12 to which the pump tube 23a of the third line 23 is attached are roller pumps, peristaltic pumps. Non-blood contact type pumps such as are preferred. As the first liquid sending pump 11 (blood pump), a pump capable of sending blood in any direction is used. Specifically, a roller pump capable of normal rotation and reverse rotation is used.

The control section collects the blood to which the anticoagulant has been added, separates the collected blood, and collects the separated plasma in a plasma collection bag, and a plasma collection step. At least one plasma collection / circulation step comprising a plasma circulation step of circulating the plasma in the plasma collection bag to the centrifuge; A platelet collection step of causing the platelets to flow out of the centrifuge and collect the platelets into the platelet collection bag, and a blood return step of returning the blood in the centrifuge after completion of the platelet collection step. It is to make it.

Specifically, the control unit 13 operates the first liquid supply pump 11 and the second liquid supply pump 12 to collect the blood to which the anticoagulant has been added, and the centrifuge drive device 10 Is operated (by rotating the rotor at the above-described calculated value or the set value) to perform a first plasma collection step of collecting a first predetermined amount of plasma from the blood into the plasma collection bag 25, Next, the blood collection is temporarily interrupted, and the centrifuge driving device 10 is operated (by rotating the rotor at the above-described calculated value or set value) to remove the plasma in the plasma collection bag from the centrifuge 20. A constant-speed plasma circulation step (constant-speed circulation) that circulates at a constant speed, and performs a plasma collection / constant-speed circulation step. Then, the first liquid supply pump 11 and the second liquid supply pump 12 Activated blood with anticoagulant added Plasma is collected by operating the centrifugal separator driving device 10 (by rotating the rotor at the above-described calculated value or set value) and detecting a predetermined position (for example, a buffy coat layer) by the interface sensor. A second plasma collection step to be performed, and after the second plasma collection step is completed, the blood collection is temporarily stopped, and the centrifuge driving device 10 is operated (the rotor is operated based on the above-described calculated value or set value. Rotating) and accelerating and circulating the plasma in the plasma collection bag 25 to the centrifugal separator 20 (accelerated circulation). A plasma collection / acceleration circulation step, and the plasma collection / circulation step ends. Later, the plasma circulation speed by the first liquid supply pump 11 is accelerated to cause the platelets to flow out of the centrifugal separator 20 and the platelets to be collected in the platelet collection bag. A platelet collection step of collecting, after the end of the platelet collection step, in which to perform blood return step of returning blood to the blood in the centrifugal separator 20. In the second plasma collection step, the weight of the plasma bag is not detected because the detection is performed by the interface sensor.

Thus, during one platelet collection operation,
The plasma recirculation step of suspending the blood collection and recirculating the collected plasma to the centrifuge is performed at least twice, and the latter half of the plasma recirculation step is accelerated circulation. In this case, the blood cell layer and the buffy coat layer (BC layer) can be suppressed from being excessively compressed, platelets buried in the red blood cell layer can be raised, and can be taken into the BC layer. Further, since the BC layer itself also rises, the separation and alignment of platelets and leukocytes in the BC layer are promoted. For this reason,
It is possible to obtain a platelet-containing liquid (rich platelet plasma) with little leukocyte contamination and high platelet collection efficiency.

Further, the blood component collecting apparatus 1 of this embodiment
The control unit 13 of the centrifugal separator driving device 10 so that the platelet collection operation including the plasma collection / constant-speed circulation step, the plasma collection / accelerated circulation step, the platelet collection It controls the first liquid feed pump 11, the second liquid feed pump 12, and a plurality of flow path opening / closing means.

Further, the blood component collecting apparatus 1 of this embodiment
After the end of the platelet collection step,
Before the blood return step, the plasma circulation speed by the first liquid feeding pump 11 is set higher than the final speed in the platelet collection step, the buffy coat is discharged from the centrifuge 20, and the buffy coat is collected in the buffy coat collection bag 27. The buffy coat collecting step is controlled to be performed. The buffy coat collecting step is not limited to the above-described method. For example, the plasma circulation speed by the first liquid feeding pump 11 is maintained at the final speed in the platelet collecting step, and the centrifuge 20 This may be performed by lowering the rotation speed of the rotor. Further, the buffy coat collecting step may be performed by making the plasma circulation speed by the first liquid feeding pump higher than the final speed in the platelet collecting step and lowering the rotation speed of the rotor of the centrifuge. Then, after the buffy coat collecting step is completed, the first liquid feeding pump 11 and the plurality of liquid feeding pumps are set so as to perform a buffy coat returning step of returning the collected buffy coat into the centrifuge 20 before the next blood collecting step. Is controlled.

The platelet collection operation will be described more specifically.
First, the blood cell component measurement is performed in advance using the sampled blood collected from the donor just before the operator starts the component blood collection. The control unit calculates the optimum rotor speed (initial rotor speed) by inputting the measured hematocrit value of the blood donor into the device. Then enter other required parameters. Then, the third line 23 and the blood collection needle 29 are primed with an anticoagulant, and thereafter, the donor is punctured with a puncture needle, and component blood collection is started. At the same time as the start of blood collection, a blood collection time measurement timer for calculating an average blood collection speed is started.

An anticoagulant is prescribed for whole blood (1 for whole blood)
/ 8 to 1/20, specifically 1/10) at a predetermined speed (250 ml / min or less; preferably 150 ml / min or less).
４０40 ml / min or less, specifically, 60 ml / mi
n or less) to the centrifugal separator 20 via the first line 21 and rotate the centrifugal separator 20 at a predetermined rotational speed [3000 to 600].
0 rpm, preferably in the range of 4400 to 5800 rpm, which is automatically calculated using the hematocrit value of the donor (initial rotor speed)] to convert blood into plasma, buffy coat, and erythrocyte components. Separation, when the plasma overflows the centrifuge 20, the blood is collected in a plasma bag, and when a predetermined amount of the plasma (10 to 150 ml, preferably 20 to 30 ml) is collected, the blood transmission is stopped.
The plasma was subjected to a predetermined condition (at a rate greater than the
10 to 90 sec at ~ 250 ml / min, specifically, the first circulation is 200 ml / min x 30 sec)
A constant-rate plasma circulation is performed returning to the centrifuge 20 through the first line 21 and the second line 22.

Then, an anticoagulant is again added to whole blood (1/8 to 1/20, specifically 1/10 with respect to whole blood).
At a predetermined rate (250 ml / min or less; preferably, 150 to 40 ml / min or less, specifically,
(60 ml / min or less) to the centrifugal separator 20 via the first line 21 to rotate the centrifugal separator 20 at a predetermined rotation speed (3
000-6000 rpm, preferably 4700-48
00 rpm) to separate blood into plasma, buffy coat, and red blood cell components. When the blood cell interface position inside the centrifuge 20 is detected by the buffy coat interface detection sensor, the blood supply is stopped. Under predetermined conditions (initial speed
80 ml / min, final arrival speed (set speed) 150 to
250 ml / min, acceleration conditions (every second) 2 to 10
ml / min speed increase, circulation time 10-90 sec)
Then, accelerated plasma circulation is performed by returning to the centrifugal separator 20 through the first line 21 and the second line 22.

The average blood collection speed (blood flow speed) is calculated from the blood collection time and the blood processing volume up to this time, and if the predetermined speed is not reached, the rotor rotational speed is calculated again as described above. The rotor rotation speed calculated at this time is used after completion of the platelet collection and buffy coat collection operations performed immediately thereafter. That is, the rotor rotation speed is changed from the blood collection step in the next cycle. Then, under predetermined conditions (blood collection amount: 100 to 2500 / Hct% [ml],
Specifically, a small amount of whole blood is collected while adding an anticoagulant again under the condition of 250 to 1000 / Hct% [ml]).

After the last blood collection, the plasma is passed through first and second lines 22 under predetermined conditions.
And stepwisely increase the acceleration under predetermined conditions (stepwise acceleration; 0.1 to 99 ml / min / sec).
c, specifically, 2 to 10 ml / min / sec) Platelet collection speed (60 to 250 ml / min; actually 200
ml / min) and collects the platelets flowing out from the centrifuge 20 into the platelet collection bag 26. Further, in this device, after collecting platelets, the blood circulation speed is maintained (60 to 250 ml / min, specifically, 200 ml / min), and the rotation speed of the centrifuge 20 is reduced (the rotation speed up to now). From 100 to 300
By lowering by about rpm, the buffy coat that has flowed out is collected, and the collected buffy coat is supplied to the centrifugal separator 20 before performing blood collection in the next cycle. In addition, the collection of buffy coat, after the platelet collection, the blood circulation speed to a predetermined speed (platelet collection speed or more,
Preferably, it is 60 to 250 ml / min, specifically,
It may be performed by accelerating to 205 ml / min). The blood component collecting step (first platelet collecting operation) by the blood component collecting apparatus 1 of this embodiment will be described with reference to the flowcharts of FIGS. In this embodiment, the platelet collection operation is repeatedly performed twice, and after the platelet collection steps other than the last one have been completed,
Before the blood return step, a buffy coat collection step is performed, and before the next blood collection step, a buffy coat return step of returning the buffy coat to the centrifuge 20 is performed. The fourth line 24 for fluid injection and the flow path opening / closing means 87 are not used.

Then, as shown in FIG. 5, the first liquid supply pump 11 and the second liquid supply pump 12 are operated to collect the blood to which the anticoagulant has been added, and the centrifugal separator driving device 10 is operated. When activated, a first plasma collection step of collecting a first predetermined amount of plasma from the blood into the plasma collection bag 25 is performed.
When the first blood collection is started, the blood pump 11 starts collecting blood at a predetermined speed (for example, 60 ml / min). At this time, the second pump, which is an anticoagulant pump, simultaneously supplies the anticoagulant (for example, ACD-A liquid) at a predetermined speed (for example, 1/10 of the blood pump speed). The blood collected from the donor is mixed with the ACD solution, flows through the first line 21, passes through the chamber, the first channel opening / closing means 81,
It flows into the centrifuge 20. At this time, the sixth flow path opening / closing means 86, the fifth flow path opening / closing means 85, the second flow path opening / closing means 82, the third flow path opening / closing means 83, and the seventh flow path opening / closing means 87 are closed. The first channel opening / closing means 81 and the fourth channel opening / closing means 84 are open. ACD in centrifuge 20
When the blood is supplied, the sterilized air entering the centrifugal separator 20 flows through the second line 22, passes through the fourth channel opening / closing means 84, and flows into the platelet collection bag 26. Simultaneously with the start of the blood collection step, the centrifugal separator 20 starts rotating at a predetermined speed (initial rotor rotational speed calculation value).
Receives the supply of ACD blood while rotating, blood is centrifuged in the separator, and blood is separated from the inside into three layers, a plasma layer, a buffy coat layer (BC layer), and a red blood cell layer, ACD blood over the capacity of the separator (about 270
ml) is supplied, the inside of the centrifuge 20 is completely filled with blood, and the plasma flows out of the outlet of the centrifuge 20. The turbidity sensor 14 attached to the second line 22 connected to the outlet of the centrifuge 20 detects that the fluid flowing in the line has changed from air to plasma, and the control unit 13 Based on the detection signal of the turbidity sensor 14, the fourth flow path opening / closing means 84 is closed and the third flow path opening / closing means 83 is opened, and the plasma is collected in the plasma collection bag 2.
Collect within 5. The weight of the plasma collection bag 25 is measured by the weight sensor 16, and the measured weight signal is input to the control unit 13. For this reason, the weight of the plasma collected in the plasma collection bag 25 is the first predetermined amount (10
To 150 g, for example, 30 g).
Closes the first flow path opening / closing means 81 and opens the second flow path opening / closing means 82 to shift to a constant-speed plasma circulation step.

In the constant-velocity plasma circulation step, the blood collection is temporarily interrupted, and the centrifugal separator driving device 10 is operated so that the plasma collected in the plasma collection bag 25 is centrifuged by the centrifugal separator 20.
At a constant speed. When entering the constant-speed plasma circulation step, the control unit 13 maintains the closed state of the first flow path opening and closing means 81 and the open state of the second flow path opening and closing means 82,
The CD pump 12 stops, and the blood pump 11 operates at a predetermined speed (60 to 250 ml / min, for example, 200 ml / m).
In), the plasma in the plasma collection bag 25 is sent to the centrifugal separator 20 rotating at a predetermined speed (initial rotor rotational speed calculation value) through the second flow path opening / closing means 82. At the same time, the plasma flowing out of the centrifuge 20
4. The plasma collection bag 2 through the third channel opening / closing means 83
Flow into 5. When a predetermined time (10 to 90 seconds, for example, 30 seconds) has elapsed since the start of the constant-speed plasma circulation step, the control unit 13 closes the second flow path opening / closing means 82 and switches the first flow path opening / closing means 81 to Open and move to the second plasma collection step. The first plasma circulation is at least 60 ml / mi
It is preferable to carry out at a flow rate of n or more for 10 seconds or more.

In the second plasma collection step, the first liquid supply pump 11 and the second liquid supply pump 12 are operated to collect the blood to which the anticoagulant has been added, and usually the amount of plasma in the bag is reduced. When the optical sensor 15 detects the buffy coat layer of the separator due to the increase, this signal is sent to the control unit 13, and the control unit 13 closes the first flow path opening / closing means 81 and closes the second flow path. The road opening / closing means 82 is opened, and the process proceeds to the accelerated plasma circulation step. Specifically, the first liquid supply pump 11 starts collecting blood at a predetermined speed (for example, 60 ml / min). At this time, the second pump, which is an anticoagulant pump, is also simultaneously driven at a predetermined speed (eg, 1/1 of the blood pump speed).
At 0), an anticoagulant (for example, ACD-A solution) is supplied.
The blood collected from the donor is mixed with the ACD solution, flows into the centrifugal separator 20 rotating at a predetermined speed (calculated value of the initial rotor speed), and collects the plasma in the plasma collection bag 25. Usually, when the optical sensor 15 detects the buffy coat layer of the separator due to an increase in the amount of plasma in the bag, this signal is sent to the control unit 13, and the control unit 13 Is closed, the second channel opening / closing means 82 is opened, and the process proceeds to the fifth accelerated plasma circulation step.
In the fifth plasma collection step, the sensor 15 detects the buffy coat (BC interface: the interface between the plasma layer and the buffy coat layer).
Plasma is collected until is detected. In the apparatus of this embodiment, as shown in the flowcharts of FIGS. 5, 7 and 9, BC
An interface is being detected, and if a BC interface is detected during the first plasma collection step, the plasma collection is interrupted and a transition is made to the accelerated plasma circulation step.

The average blood collection speed (blood flow speed) is calculated from the blood collection time and the blood processing volume up to this time. Calculate the corrected rotor speed calculation value.
The rotor rotation speed calculated at this time is used after completion of the platelet collection and buffy coat collection operations performed immediately thereafter. That is, the rotor rotation speed is changed from the blood collection step in the next cycle.

In the accelerated plasma circulation step, the blood collection is temporarily interrupted, and the centrifuge driving device 10 is operated to circulate the plasma in the plasma collection bag 25 to the centrifuge 20 while accelerating. At this time, the blood pump speed is lower than the constant speed plasma circulation step, for example, 60 ml / mi.
n and the final speed is 150-200 ml / mi
Accelerate until n is reached. The acceleration conditions are as follows: a speed of 2 to 10 ml / min increases every second, 200 m
It is performed with an arrival time of 1 / min about 14 to 70 seconds. After the end of this circulation step, the process proceeds to FIG. 6, and a small amount plasma collection step for interface adjustment is performed.

As shown in FIG. 6, in the step of collecting a small amount of plasma for adjusting the interface, in order to keep the position of the buffy coat layer constant in the subsequent platelet collecting step regardless of the donor,
Blood is collected for a predetermined supply amount of red blood cells. The red blood cell supply amount is defined as a value obtained by dividing the blood collection amount by the hematocrit value of the donor, and the blood collection amount is generally about 12 ml. Also in this blood collection, the first liquid supply pump 11 starts blood collection at a predetermined speed (for example, 60 ml / min). At this time,
The second pump, which is an anticoagulant pump, simultaneously supplies an anticoagulant (for example, ACD-A liquid) at a predetermined speed (for example, 1/10 of the blood pump speed). The blood collected from the donor is mixed with the ACD solution, and flows into the centrifuge 20 rotating at a predetermined speed (calculated value of the initial rotor speed).
A small plasma collection is performed. The control unit 13 calculates the collection time from the set collection amount and the pump speed, and ends the blood collection when the collection time has elapsed. Then, the control unit 13 closes the first flow path opening / closing means 81 and opens the second flow path opening / closing means 82, and shifts to a platelet collection step.

After the above steps are completed, the circulating speed of the plasma by the first liquid feed pump 11 is accelerated, and the centrifuge 20
Platelets are drained from the inside and platelets are collected in a platelet collection bag 26.
A platelet collection step of collecting platelets. The platelet collection step is also called a so-called acceleration process. In this step, the blood pump speed is, in this example, 60 ml /
The control unit 13 operates the blood pump so as to accelerate the blood pump from 10 min / min to 200 ml / min every predetermined time (for example, 1 second) by 10 ml / min.
Once in is reached, the speed is maintained until the platelet collection step is completed.

When the platelet collection step starts, the turbidity sensor 14 detects the turbidity of the liquid passing therethrough, and the turbidity is output as a voltage value by the sensor.
3 is input. When the speed of the blood pump increases and reaches approximately 160 to 200 ml / min, platelets contained in the buffy coat layer remaining in the centrifuge 20 flow out. When the platelets flow out, the turbidity of the liquid passing through the turbidity sensor 14 increases, and when the voltage value output from the sensor drops by 0.2 V, the third flow path opening / closing means 83 closes and the fourth flow The path opening / closing means 84 is opened, and platelet-rich plasma flowing out of the centrifuge 20 is collected in the platelet collection bag 26. The voltage value output from the turbidity sensor 14 is converted into a platelet concentration by the control unit 13, and the platelet concentration in the platelet collection bag 26 during platelet collection is calculated. The platelet concentration in the platelet collection bag 26 once reaches the maximum concentration and then decreases. At the point in time when it is detected that the maximum concentration has been reached, the platelet collection step ends, and the process proceeds to the buffy coat collection step.

In the buffy coat collecting step, when the above-described platelet collecting step is completed, the control unit 13
Is closed, and the fifth channel opening / closing means 85 is opened. The blood plasma in the plasma collection bag 25 is sent to the centrifugal separator 20 by the blood pump 11, and the liquid (the buffy coat layer has flowed out) from the centrifuge 20 simultaneously flows into the buffy coat collection bag 27. .
In the buffy coat collection step, the speed of the blood pump 11 is maintained at the final speed in the platelet collection step, and the centrifugal separator 20 is rotated at a predetermined speed or a slightly higher rotation speed (50 to 20 rotations than the predetermined speed).
The rotation speed is increased to about 0 rpm, for example, a rotation speed higher than 100 rpm, whereby the buffy coat flows out from the centrifuge 20 and is collected in the buffy coat collection bag 27. At the time when the amount calculated from the hematocrit value of the donor and the amount of collected platelets is collected, the blood pump 11 stops,
All valves are closed, the rotation of the centrifuge 20 stops, and the buffy coat collection step ends.

Next, a blood return step of returning the blood in the centrifuge 20 is performed. The control unit 13 rotates the blood pump 11 in the reverse direction, opens the first channel opening / closing unit 81,
The red blood cell layer remaining in the centrifuge 20 is transferred to the first line 2
Blood is returned to the donor from 1. This is the first time (first time)
Is completed. Then, as shown in FIG.
Move to the second platelet collection operation. First, as shown in FIG. 7, the buffy coat collected by the first platelet collection operation was centrifuged into a centrifuge 2 before the next plasma collection step.
A buffy coat return step of returning within 0 is performed. When the process proceeds to the buffy coat return step, the control unit 13 rotates the centrifuge 20 at a predetermined rotation speed (initial rotor rotation speed calculation value), and controls the fifth flow passage opening / closing device 85 and the fourth flow passage opening / closing device 84. Is opened, and the blood pump 11 is operated at a predetermined speed (the default is 100 ml / min). The buffy coat contained in the buffy coat collection bag 27 is supplied to the centrifugal separator 20 through the fifth channel opening / closing means 85. The air in the centrifuge 20 is sent to the platelet collection bag 26 through the second line 22 and the fourth channel opening / closing means 84. After the blood pump 11 rotates by the amount of the buffy coat collected, the buffy coat return step ends.

If the average blood collection speed (blood flow speed) in the first plasma collection step does not reach the predetermined speed, the corrected rotor speed is calculated and corrected as shown in FIG. At the rotation speed of the rotor, a first plasma collection step, a constant-speed plasma circulation step, a second plasma collection step, and an accelerated plasma circulation step are performed, and the process proceeds to FIG. The buffy coat collection step and the blood return step are sequentially performed, and the second platelet collection operation is completed.

Next, the final platelet collection operation shown in FIG. 9 will be described. In this embodiment, the third time is the final time, but the present invention is not limited to this, and the fourth and subsequent times may be the final time of the platelet collection operation. in this case,
Except for the last round, it is the same as the second platelet collection operation (FIGS. 7 and 8). First, as shown in FIG. 9, a buffy coat return step of returning the buffy coat collected by the second platelet collection operation into the centrifuge 20 before the next plasma collection step is performed. When the process proceeds to the buffy coat return step, the control unit 13 rotates the centrifuge 20 at a predetermined rotation speed (for example, 4800 rpm), and controls the fifth channel opening / closing unit 85 and the fourth channel opening / closing unit 84.
, And set the blood pump 11 to the predetermined speed (default is 1
(00 ml / min). The buffy coat contained in the buffy coat collection bag 27 is supplied to the centrifugal separator 20 through the fifth channel opening / closing means 85. The air in the centrifuge 20 is sent to the platelet collection bag 26 through the second line 22 and the fourth channel opening / closing means 84. After the blood pump 11 rotates by the amount of the buffy coat collected, the buffy coat return step ends.

Next, the first liquid feed pump 11 and the second liquid feed pump 12 are operated to collect the blood to which the anticoagulant has been added, and the centrifuge driving device 10 is operated to remove the blood. A first plasma collection step of collecting a first predetermined amount of plasma in the plasma collection bag 25 is performed. When the first blood collection is started, the first liquid supply pump 11 operates at a predetermined speed (for example, 60
(ml / min). At this time, the second pump, which is an anticoagulant pump, also has a predetermined speed (for example,
Anticoagulant (eg, AC at 1/10 of the blood pump speed)
(DA solution). The blood collected from the donor is A
The mixture is mixed with the CD solution, flows through the first line 21, passes through the chamber, the first channel opening / closing means 81, and
Flows into. At this time, the sixth channel opening / closing means 86 and the fifth
, The second channel opening / closing unit 82, the third channel opening / closing unit 83, and the seventh channel opening / closing unit 87 are closed, and the first channel opening / closing unit 81 and the fifth channel opening / closing unit 87 are closed. Channel opening / closing means 85
Is open, and when the ACD blood is supplied to the centrifuge 20, the sterilized air originally contained in the centrifuge 20 passes through the line sensor, the fifth flow path opening / closing means 85, and the buffy coat collection bag 27. Flows into. Simultaneously with the start of the blood collection process, the centrifugal separator 20 starts rotating at a predetermined speed (if the corrected rotor rotational speed has been calculated, if it has not been calculated, otherwise the initial rotor rotational speed calculated value). 20 receives the supply of ACD blood while rotating, the blood is centrifuged in the separator, and the blood is separated from the inside into three layers, a plasma layer, a buffy coat layer (BC layer), and a red blood cell layer. ACD blood over the capacity of the separator (about 2
70 ml), the inside of the centrifuge 20 is completely filled with blood, and the plasma flows out from the outlet of the centrifuge 20. The second connected to the outlet of the centrifuge 20
The turbidity sensor 14 attached to the line 22 detects that the fluid flowing in the line has changed from air to plasma, and the control unit 13 performs the fifth operation based on the detection signal of the turbidity sensor 14. The flow path opening / closing means 85 is closed, and the third
Is opened, and the plasma is collected in the plasma collection bag 25. The weight of the plasma collection bag 25 is measured by the weight sensor 16, and the measured weight signal is input to the control unit 13. Therefore, when the weight of the plasma collected in the plasma collection bag 25 increases by a predetermined amount (for example, 30 g), the control unit 13 closes the first channel opening / closing unit 81 and sets the second channel opening / closing unit 82 to Release and move to constant-speed plasma circulation step.

And the above-described constant-speed plasma circulation step,
A second plasma collection step and an accelerated plasma circulation step are performed, and the process proceeds to FIG. 10 to sequentially perform a small-volume plasma collection step for interface adjustment, a platelet collection step, and a blood return step, and the final platelet collection operation is completed. I do. Final round and 2
The difference from the first time is that the bag in which air flows in the above-mentioned constant-speed plasma circulation step is different, and in the last time, the blood return step is performed without performing the buffy coat collection step.

For a particle suspension, it is known that the higher the particle concentration, the higher the apparent viscosity of the suspension. The higher the viscosity, the smaller the difference in settling velocity between particles with different specific gravities. When this is applied to the platelet collection step, as the viscosity in the centrifuge 20 increases, the probability that white blood cells having a higher specific gravity than platelets flow out together with platelets increases. During blood collection, the centrifuge 20 is rotating, and the blood components in the centrifuge 20 are constantly subjected to centrifugal force. From the outside of the vessel, it is separated into a blood cell layer, a buffy coat layer, and a plasma layer as shown in FIG. The particles in each layer are sequentially smaller from the outside.

A plurality of cake layers are formed in the centrifugal separator 20, and the cake layers are gradually compressed.
Then, the newly flowing whole blood flows in from the cake layer formed by the outermost blood cells of the centrifugal separator 20, and the blood cells are caught by this cake layer and other components pass through, and the buffy coat layer and the plasma layer Move to However, when the blood cell cake layer and the buffy coat cake layer are excessively compressed, the gap between the fine particles in each layer becomes small, and platelets are trapped in the blood cell cake layer or the buffy coat cake layer. For this reason, it is expected that the collection efficiency of platelets will decrease.

However, according to the present invention, the plasma collection step can be divided and the time of the first plasma collection step can be shortened. In addition, by performing the accelerated plasma circulation step after the second plasma collection step, the above-described compression of the cake layer can be achieved. Is difficult to progress. In particular, by using the accelerated plasma circulation step, even if the final reaching circulation speed is high, the cake layer is hardly compressed, and platelets buried in the red blood cell layer can be raised and taken into the BC layer. Also, BC
The layer itself also soars, promoting separation and alignment of platelets and leukocytes in the BC layer. Thus, the collection efficiency of platelets is improved.

Next, the blood component collecting apparatus 100 of the embodiment shown in FIG. 11 will be described. This blood component collection device 1
00 is the same as the above-described blood component collection device 1 except that it has a hematocrit value measurement function, and the same parts are denoted by the same reference numerals, and the description refers to the above-described blood component collection device 1. Specifically, the blood component collection device 100
Is a sensor 101 constituting a hematocrit value measurement function.
The sensor 101 is electrically connected to the control unit 13. As the sensor 101, for example, 800
A device using infrared light having a wavelength of nm and utilizing its absorbance (for example, a device having a function of irradiating infrared light of 800 nm and receiving reflected light or transmitted light) can be used. Further, those proposed in JP-A-62-265563 may be used. The sensor 101 has a connection 2 with a first line 21 for accurate hematocrit measurement and a third line 23 for anticoagulant injection.
It is provided at a position closer to the blood collection needle 29 than 1c. Specifically, the sensor 101 is the first line 21, between the branch pipe 21 c, which is the connection part with the third line 23, which is the anticoagulant addition line, and the blood collection needle 29 (in the vicinity of the branch pipe). ) Is located. For this reason, the hematocrit value of the blood before the anticoagulant is added is measured.

The sensor 101 is not directly connected to the control unit, but includes a sensor 101 and a hematocrit value measuring main unit for calculating a hematocrit value from the detection result thereof. The hematocrit value measurement main unit and the control unit may be connected so that the hematocrit value is input to the control unit 13. In the blood component collection device 100, the control unit 13 uses the hematocrit value measured by the above function to calculate a rotor rotation speed suitable for the hematocrit value, and a plasma collection step. At the time of plasma collection and constant circulation step,
In the second plasma collection step and the plasma collection / acceleration circulation step, the centrifuge driving device is controlled so that the rotor is rotated at the rotor rotation speed calculated by the rotor rotation speed calculation function. Further, similarly to the above-described embodiment, when the average blood collection speed (blood flow speed) at the time of the first plasma collection step does not reach the predetermined speed, the corrected rotor rotation speed is calculated as described above, At the corrected rotor speed, at the time of the plasma collection step in the second and subsequent plasma collection steps, during the plasma collection and constant-speed circulation step,
In the second plasma collection step and the plasma collection / acceleration circulation step, the centrifugal separator driving device is controlled so that the rotor is rotated at the corrected rotor speed calculated again by the rotor speed calculation function.

The blood component collecting step (first platelet collecting operation) by the blood component collecting apparatus 100 of this embodiment will be described with reference to the flowcharts of FIGS.
Also in this embodiment, the platelet collection operation is repeatedly performed twice, and further, after the end of the platelet collection step other than the last one, before the blood return step, the buffy coat collection step is performed, and before the next blood collection step. A buffy coat return step for returning the buffy coat to the centrifuge 20 is performed. First, the third line 23 and the blood collection needle 29 are primed with an anticoagulant, and then the donor is punctured with a puncture needle.

By operating the first liquid supply pump 11 and the second liquid supply pump 12, the first line 2
1, blood is supplied from the donor and the sensor 10
The hematocrit value related signal detected by 1 is sent to the control unit 13, and the control unit 13 calculates the hematocrit value using the hematocrit value related signal. Further, based on the calculated hematocrit value, the calculation unit calculates an appropriate rotor speed. The centrifugal separator driving device 10 performs a first plasma collection step of rotating the rotor at the calculated value and collecting a first predetermined amount of plasma from the blood into the plasma collection bag 25.

When the first blood collection is started, the blood pump 1
1 starts blood collection at a predetermined speed (for example, 60 ml / min). At this time, the second pump, which is an anticoagulant pump, is also simultaneously driven at a predetermined speed (eg, 1/1 of the blood pump speed).
At 0), an anticoagulant (for example, ACD-A solution) is supplied.
Blood collected from the donor is mixed with ACD fluid and
, Passes through the chamber and the first channel opening / closing means 81, and flows into the centrifuge 20. At this time,
Sixth flow path opening / closing means 86, fifth flow path opening / closing means 85, second flow path opening / closing means 82, third flow path opening / closing means 83, seventh flow path
The first channel opening / closing means 81 and the fourth channel opening / closing means 84 are open. When the ACD blood is supplied to the centrifuge 20, the centrifuge 20
The sterile air that has entered flows through the second line 22 and
, And flows into the platelet collection bag 26. The rotor of the centrifugal separator 20 starts rotating at the calculated value (for example, 4800 rpm) at the same time as the start of the blood collection process, and the centrifugal separator 20 receives the supply of ACD blood while rotating. Is done,
Blood is applied from the inside to the plasma layer and buffy coat layer (BC
Layer) and red blood cell layer, and when ACD blood (about 270 ml) exceeding the capacity of the separator is supplied, the inside of the centrifuge 20 is completely filled with blood, and the flow of the centrifuge 20 Plasma flows out of the outlet. The turbidity sensor 14 attached to the second line 22 connected to the outlet of the centrifuge 20 detects that the fluid flowing in the line has changed from air to plasma, and the control unit 13 The fourth flow path opening / closing means 84 is closed based on the detection signal of the turbidity sensor 14, and the third flow path opening / closing means 83 is opened,
Plasma is collected in the plasma collection bag 25. The weight of the plasma collection bag 25 is measured by the weight sensor 16, and the measured weight signal is input to the control unit 13. For this reason, the weight of the plasma collected in the plasma collection bag 25 is the first predetermined amount (10 to 150 g, for example, 20 g).
When it increases, the control unit 13 closes the first flow path opening / closing means 81 and opens the second flow path opening / closing means 82, and shifts to a constant-speed plasma circulation step.

After the transition to the constant-speed plasma circulation step, the operation is the same as that in the first embodiment. After the end of the second plasma collection step, the average blood collection speed (blood flow speed) is calculated from the blood collection time and the blood processing volume up to this time. Recalculate the number. The rotor rotation speed calculated at this time is used after completion of the platelet collection and buffy coat collection operations performed later. That is, the rotor rotation speed is changed from the blood collection step in the next cycle. Then, an accelerated plasma circulation step is performed, and after the accelerated plasma circulation step,
Shifting to FIG. 6, a small-volume plasma collection step for interface adjustment is performed. Subsequent steps are the same as those of the embodiment described with reference to the flowcharts shown in FIGS. 6 to 10 and FIGS.

In this embodiment, FIGS.
Since the rotation speed is set to 0, the rotation speed of the rotor is controlled when necessary by the initially calculated rotor rotation speed (initial rotor rotation speed calculation value) or the corrected rotor rotation speed calculation value. Also, at the time of the second blood sampling, the hematocrit value is measured, the rotor speed is again calculated using the newly measured hematocrit value and the blood flow speed, and the second and subsequent plasma collection steps are performed. Alternatively, a newly calculated rotor rotation speed may be used. Further, when there is a third or subsequent plasma collection step, the hematocrit value is measured each time, and the newly calculated rotor rotation speed ( The latest rotor rotational speed calculation value) may be used.

Next, a blood component collecting apparatus according to another embodiment of the present invention will be described. This blood component collection device has a hematocrit value measurement function using a centrifuge, and uses this function to measure the hematocrit value during the first plasma collection step, and to use the measured hematocrit value to determine the hematocrit value. Rotor rotation speed calculation function to calculate the rotor rotation speed suitable for the motor, and to rotate the rotor at the rotor rotation speed calculated by the rotor rotation speed calculation function during the second plasma collection step and the plasma collection and acceleration circulation step To control the centrifuge driving device. The basic configuration is the same as the blood component collection device 1 shown in FIG.

A method for measuring a hematocrit value using a centrifuge is, for example, the following method. As the optical sensor 15, an optical sensor that can scan vertically along the outer peripheral surface of the centrifuge 20 is used (specifically, five optical sensors are linearly arranged in the vertical direction). ). Then, using these sensors, the centrifuge 2
The position of the blood cell interface at 0 is measured. The measured boundary signal is converted by the control unit into xi (i = 0 to n,
(n is an integer determined by the resolution capability of the optical sensor). Note that x0 is a state where no interface is detected, and xn is a state where the entire inside of the centrifuge 20 is filled with blood cells. If the shape and volume of the centrifuge are known, and the blood collection rate (blood removal rate), the anticoagulant injection rate, and the rotor are also constant, the following correlation between xi and hematocrit (Hct) is obtained. The equation Hct (%) = F (xi) holds, and the control unit stores the correlation equation. For this reason, the control unit has a hematocrit value calculation function using the signal xi obtained from the sensor 15. Note that, in the above correlation equation, correction is performed in consideration of the blood removal rate from the donor and the anticoagulant infusion rate, and the value calculated by the control unit is not the hematocrit value of ACD blood addition, but is substantially This is the actual hematocrit value.

The blood component collecting step (first platelet collecting operation) by the blood component collecting apparatus of this embodiment will be described with reference to the flowchart of FIG. In this embodiment, the platelet collection operation is repeated twice, and further, after the end of the platelet collection step other than the last one, before the blood return step, the buffy coat collection step is performed, and before the next blood collection step. A buffy coat return step for returning the buffy coat to the centrifuge 20 is performed. First, the third line 23 and the blood collection needle 29 are primed with an anticoagulant, and then the donor is punctured with a puncture needle. The first liquid feed pump 11 and the second liquid feed pump 12 are operated to collect blood to which the anticoagulant has been added, and the centrifuge drive device 1
0 performs the first plasma collection step of rotating the rotor at the set rotation number stored by the control unit and collecting a first predetermined amount of plasma from the blood into the plasma collection bag 25.

When the first blood collection is started, the blood pump 1
1 starts blood collection at a predetermined speed (for example, 60 ml / min). At this time, the second pump, which is an anticoagulant pump, is also simultaneously driven at a predetermined speed (eg, 1/1 of the blood pump speed).
At 0), an anticoagulant (for example, ACD-A solution) is supplied.
Blood collected from the donor is mixed with ACD fluid and
, Passes through the chamber and the first channel opening / closing means 81, and flows into the centrifuge 20. At this time,
Sixth flow path opening / closing means 86, fifth flow path opening / closing means 85, second flow path opening / closing means 82, third flow path opening / closing means 83, seventh flow path
The first channel opening / closing means 81 and the fourth channel opening / closing means 84 are open. When the ACD blood is supplied to the centrifuge 20, the centrifuge 20
The sterile air that has entered flows through the second line 22 and
, And flows into the platelet collection bag 26. The rotor of the centrifugal separator 20 starts rotating at a set value (for example, 4800 rpm) simultaneously with the start of the blood collection step, and the centrifugal separator 20 receives the supply of ACD blood while rotating. Then, the hematocrit value is calculated using the optical sensor 15 attached to the centrifuge 20. Then, using the calculated hematocrit value, the rotor proper rotation speed is further calculated.

In the centrifuge 20, the blood is centrifuged, and the blood is separated from the inside into three layers, a plasma layer, a buffy coat layer (BC layer), and a red blood cell layer, and the capacity of the separator is reduced. When the excess ACD blood (about 270 ml) is supplied, the inside of the centrifuge 20 is completely filled with blood,
Plasma flows out of the outlet of the centrifuge 20. The turbidity sensor 14 attached to the second line 22 connected to the outlet of the centrifuge 20 detects that the fluid flowing in the line
Upon detecting that the air has changed to plasma, the control unit 13
Based on the detection signal of the turbidity sensor 14, the fourth flow path opening / closing means 84 is closed and the third flow path opening / closing means 83 is opened, and the plasma is collected in the plasma collection bag 25. The weight of the plasma collection bag 25 is measured by the weight sensor 16, and the measured weight signal is input to the control unit 13. For this reason, when the weight of the plasma collected in the plasma collection bag 25 increases by the first predetermined amount (10 to 150 g, for example, 20 g), the control unit 13 closes the first flow path opening / closing means 81, and Then, the flow path opening / closing means 82 is opened to shift to a constant-speed plasma circulation step.

In the constant-velocity plasma circulation step, the blood collection is temporarily stopped, and the centrifugal separator driving device 10 is operated to maintain the rotation of the rotor of the centrifugal separator 20 at the set value. The collected plasma is circulated through the centrifuge 20 at a constant speed. When entering the constant-speed plasma circulation step,
The controller 13 maintains the closed state of the first channel opening / closing means 81 and the open state of the second channel opening / closing means 82,
The pump stops, and the blood pump 11 operates at a predetermined speed (60 to 2).
It operates at 50 ml / min (for example, 200 ml / min), and the plasma in the plasma collection bag 25 is sent to the centrifugal separator 20 rotating at a set value (for example, 4800 rpm) through the second flow path opening / closing means 82. Can be At the same time, the plasma flowing out of the centrifuge 20 flows into the plasma collection bag 25 through the turbidity sensor 14 and the third channel opening / closing means 83. After the constant-speed plasma circulation step has started,
After 90 seconds (for example, 30 seconds) elapse, the control unit 13
Closes the second flow path opening / closing means 82, opens the first flow path opening / closing means 81, and shifts to the second plasma collection step.
The first plasma circulation is preferably performed at a flow rate of at least 60 ml / min or more for 10 seconds or more.

In the second plasma collection step, the first liquid supply pump 11 and the second liquid supply pump 12 are operated to collect the blood to which the anticoagulant has been added, and to increase the amount of plasma in the bag. When the optical sensor 15 detects the buffy coat layer of the separator, this signal is sent to the control unit 13, and the control unit 13 closes the first flow path opening / closing means 81 and opens / closes the second flow path. The means 82 is opened to move to the accelerated plasma circulation step. Specifically, the first liquid supply pump 11 starts collecting blood at a predetermined speed (for example, 60 ml / min).
At this time, the second pump, which is an anticoagulant pump, simultaneously supplies the anticoagulant (for example, ACD-A liquid) at a predetermined speed (for example, 1/10 of the blood pump speed). Blood collected from the donor is mixed with the ACD solution, flows into the centrifuge 20 with the rotor rotating at a set value (for example, 4800 rpm), and plasma is collected in the plasma collection bag 25. Usually, when the optical sensor 15 detects the buffy coat layer of the separator due to an increase in the amount of plasma in the bag, this signal is sent to the control unit 13, and the control unit 13 Is closed, the second flow path opening / closing means 82 is opened, and the process proceeds to the accelerated plasma circulation step. In the plasma collection step, the sensor is buffy coat (BC interface:
Plasma is collected until the detection of the interface between the plasma layer and the buffy coat layer). In the apparatus of this embodiment, FIG.
As shown in the flowcharts of FIGS. 7 and 9, in each of the first to final plasma collection steps,
If a BC interface is detected during these first to last plasma collection steps,
Interrupt plasma collection and move to accelerated plasma circulation step.

The average blood collection speed (blood flow speed) is calculated from the blood collection time and the blood processing volume up to this time, and if the predetermined speed is not reached, the rotor rotation speed is recalculated as described above. The rotor rotation speed calculated at this time is used after completion of the platelet collection and buffy coat collection operations performed later. That is, the rotor rotation speed is changed from the blood collection step in the next cycle. In the accelerated plasma circulation step, the blood collection is temporarily stopped, and the centrifugal separator driving device 10 is operated to maintain the rotation of the centrifuge 20 at the set value of the rotor. Circulation is accelerated through the centrifuge 20. The blood pump speed at this time is lower than the constant speed plasma circulation step, for example, starts at 60 ml / min, and accelerates until the final speed reaches 200 ml / min. The acceleration is performed at a speed of 6.7 ml / min every second, and a 200 ml / min arrival time of about 21 seconds.
After the end of this circulation step, the process proceeds to FIG. 6, and a small amount plasma collection step for interface adjustment is performed.

The subsequent steps are the same as those in the flowcharts shown in FIGS. 6 to 10 and the first embodiment described above with reference to FIGS. 6 to 10, and the rotor of the centrifuge 20 is
Unlike the first step, when the blood flow velocity in the first plasma collection operation is larger than a predetermined value, the normal rotor rotation number calculated from the hematocrit value measured initially, and When the blood flow velocity in the first plasma collection operation is equal to or less than a predetermined value, the rotor is rotated by using the calculated hematocrit value and the corrected rotor rotational speed calculation value calculated in consideration of the blood flow velocity. . Furthermore, if there is a third or subsequent plasma collection step, the hematocrit value is also measured using a centrifuge during the second plasma collection step, and the measured value is used to calculate the normal rotor rotation speed or the corrected rotor. The rotation speed calculation value may be newly calculated, and the third and subsequent plasma collection steps may be performed using the calculation value and the rotor rotation speed (the latest rotor rotation speed calculation value number).

[0085]

EXAMPLE An apparatus comprising two units, an ACD pump 12 and a blood pump 11, was manufactured with the circuit configuration shown in FIG. 4, and the platelet collection performance was compared. Comparative experiments were performed using the same donor at intervals of 2 weeks or more. A comparison of the operation flows evaluated below is shown. n = 2
Examples were compared. The platelet count and leukocyte count of the obtained concentrated platelet plasma were measured using Sysmex (R) NE-6000. However, the lower limit of WBC measurement of Sysmex is 0.1 × 1.
Since it is 0 ² [Cells / muL], the sample below the lower limit of measurement was measured using the Agegotte [1: 9] method. The amount of platelets collected was 40 ml.

(Example 1) The platelet collection operation was performed three times, and was performed by the above-described method. The blood collection speed was 40
ml / min, the first performed after the total amount of plasma reaches 30 g
Circulation conditions (200 ml / min, 30 sec), second circulation conditions (initial speed 60 ml / min,
Achieving speed 170ml / min, acceleration condition 5ml / min
/ Sec, acceleration time 22 sec), acceleration conditions during platelet collection (10 ml / min / sec), platelet collection speed (200 ml / min, up to a predetermined concentration of platelet collection), buffy coat collection speed (195 ml / min, 30 m)
In the second and third times, the buffy coat was returned to the centrifuge before blood collection, and the third time, no buffy coat was collected. Correlation formula described above y ⁼ 0.0667x ³ -8.7619x 2 +391.9
When the corrected rotor speed calculation value was calculated from x-1277.4-D and y ≧ 4400, the minimum rotor speed was 4400 rpm (Hct = 35%).
It became.

(Comparative Example) As the apparatus, the same apparatus as in the example was used. The platelet collection operation was performed three times, the blood collection rate was 40 ml / min, and the first circulation condition (200 ml / min, 30 sec) performed after the total amount of plasma was 30 g.
c), the second circulation condition (initial speed 60 m
1 / min, arrival speed 170 ml / min, acceleration condition 5
ml / min / sec, acceleration time 22 sec), acceleration conditions during platelet collection (10 ml / min / sec), platelet collection speed (200 ml / min, up to a predetermined concentration of platelet collection), buffy coat collection speed (195 ml / mi)
n, 30 ml), the buffy coat was returned to the centrifuge before blood collection for the second and third times, and the buffy coat was not collected for the third time. Centrifugal rotation speed is 480
It was set to 0 rpm (Hct = 35%). And the platelet concentration of the concentrated platelet plasma of the collected Example and Comparative Example,
Leukocyte concentration and blood processing volume are as follows.

[0088]

[Table 1]

[0089]

[Table 2]

[0090]

[Table 3]

[0091]

According to the blood component collecting apparatus of the present invention, the control section has a function of controlling the centrifugal rotation speed of the rotor of the centrifugal separator according to the blood flow speed at the time of blood collection by the blood donor. For example, by changing the rotor rotation speed in consideration of the blood flow speed at the time of blood collection of a donor, excessive compression of the separated blood component layer due to excessive centrifugation called packing may occur in the case of a donor with a low blood flow rate. Can be prevented. When such packing occurs, the platelet layer is also compressed, so that platelet collection is difficult and collection efficiency is reduced. Conversely, in the case of a blood donor having a high hematocrit value, it is possible to prevent a state of insufficient separation due to insufficient centrifugation. When such an insufficiently separated state occurs, many platelets not located in the platelet layer are present in the blood cell layer or plasma, and the collection efficiency is reduced. However, in the apparatus of the present invention, the occurrence of the above-described packing phenomenon and insufficient separation is extremely reduced, and efficient platelet collection can be performed.

[Brief description of the drawings]

FIG. 1 is a plan view showing a configuration example of a blood component collection circuit used in a blood component collection device of the present invention.

FIG. 2 is a plan view of a cassette housing part of the blood component collection circuit of FIG. 1;

FIG. 3 is a partially broken cross-sectional view showing a state in which a driving device is mounted on a centrifuge used in a blood component collection circuit.

FIG. 4 is a conceptual diagram of one embodiment of a blood component collecting apparatus of the present invention in a state where a blood component collecting circuit is mounted.

FIG. 5 is a flowchart for explaining the operation of the blood component collecting apparatus of the present invention.

FIG. 6 is a flowchart for explaining the operation of the blood component collecting apparatus of the present invention.

FIG. 7 is a flowchart for explaining the operation of the blood component collecting apparatus of the present invention.

FIG. 8 is a flowchart for explaining the operation of the blood component collecting apparatus of the present invention.

FIG. 9 is a flowchart for explaining the operation of the blood component collecting apparatus of the present invention.

FIG. 10 is a flowchart for explaining the operation of the blood component collecting apparatus of the present invention.

FIG. 11 is a conceptual view of another embodiment of the blood component collecting apparatus of the present invention with the blood component collecting circuit mounted.

FIG. 12 is a flowchart for explaining the operation of the blood component collecting apparatus of the present invention.

FIG. 13 is a flowchart for explaining the operation of the blood component collecting apparatus of the present invention.

[Explanation of symbols]

 Reference Signs List 1 blood component collecting device 2 blood component collecting circuit 10 centrifuge driving device 11 first liquid feed pump 12 second liquid feed pump 13 control unit 14 turbidity sensor 15 optical sensor 16 weight sensor 20 centrifuge 21 1 line 22 2nd line 23 3rd line 24 4th line 25 Plasma collection bag 26 Platelet collection bag 29 Blood collection needle 100 Blood component collection device

──────────────────────────────────────────────────続 き Continued on the front page (51) Int.Cl. ⁷ Identification symbol FI Theme coat ゛ (Reference) G01N 1/14 G01N 1/14 A // G01N 33/48 33/48 C

Claims (12)

[Claims] A rotor having a blood storage space therein, an inlet and an outlet communicating with the blood storage space, and centrifuging blood introduced from the inlet by rotation of the rotor in the blood storage space. A first line for connecting a centrifuge to be separated, a blood collection needle or a blood collection device connection portion to an inlet of the centrifuge, and a second line connected to the outlet of the centrifuge A third line connected to the first line for injecting an anticoagulant; a second tube connected to the first line and a second line connected in the middle of the first line; A blood component collection device comprising a blood component collection circuit comprising a plasma collection bag having a tube and a platelet collection bag connected to the second line, wherein the blood component collection device is used when a blood donor collects blood. Blood flow velocity Therefore, the blood component collection apparatus characterized by a control unit having a function of changing a centrifugal rotation speed of the rotor of the centrifuge. 2. The control unit has a function of changing a centrifugal rotation speed of a rotor of the centrifugal separator according to a blood component concentration of the blood donor and a blood flow speed at the time of blood collection of the blood donor. 2. The blood component collection device according to 1. 3. The blood component collection device according to claim 2, wherein the blood component concentration of the donor is a hematocrit value. 4. The centrifuge driving device for rotating the rotor of the centrifuge, the centrifuge driving device for rotating the rotor of the centrifuge, and a centrifugal separator side with respect to a connection between the first line and the first tube. A first liquid supply pump for the first line, a second liquid supply pump for the third line, and a circuit for opening and closing the flow path of the blood component collection circuit. A plurality of flow path opening / closing means, and a control unit for controlling the centrifugal separator driving device, the first liquid feeding pump, the second liquid feeding pump, and the plurality of flow path opening / closing means, The control unit is configured to collect the blood to which the anticoagulant is added, to separate the collected blood and to collect the separated plasma in the plasma collection bag, and to collect the plasma collected in the plasma collection step. The plasma in the plasma collection bag At least one plasma collection / circulation step comprising a plasma circulation step of circulating the blood through the heart separator, and after the plasma collection / circulation step, by accelerating the plasma circulation speed by the first liquid feeding pump, A platelet collection step is performed to cause the platelets to flow out of the centrifuge and collect the platelets in the platelet collection bag. 4. The apparatus according to claim 1, wherein the centrifugal separator driving device, the first liquid supply pump, the second liquid supply pump, and the plurality of flow path opening / closing means are controlled so that a platelet collection operation is performed. The blood component collection device according to any one of the above. 5. The method according to claim 1, wherein after the plasma collection and circulation step is completed, the control unit increases the plasma circulation speed by the first liquid supply pump,
Activating the second liquid supply pump to collect blood to which the anticoagulant has been added, and operating the centrifugal separator driving device to collect a predetermined amount of plasma from the blood into the plasma collection bag The blood component collecting apparatus according to claim 4, wherein the blood component collecting apparatus performs the steps. 6. The control section controls the plasma collection / circulation step to be performed twice. In an initial plasma collection / circulation step, the plasma in the plasma collection bag is separated by the centrifugal separator. Plasma collection at constant speed
A constant-speed circulation step is performed, and in the second plasma collection / circulation step, control is performed such that a plasma collection / accelerated circulation step of circulating plasma in the plasma collection bag while accelerating the plasma in the centrifuge is performed. The blood component collection device according to claim 4 or 5, wherein 7. The blood component collection circuit includes a buffy coat collection bag connected to the second line, wherein the control unit is provided after the platelet collection step,
The blood according to any one of claims 3 to 6, wherein a buffy coat collecting step is performed before the blood returning step, in which the buffy coat is discharged from the centrifuge and the buffy coat is collected in the buffy coat collecting bag. Component sampling device. 8. When the platelet collection operation is further performed after the completion of the buffy coat collection step, the control unit stores the collected buffy coat in the centrifuge before the next plasma collection / circulation step. 8. The blood component collection device according to claim 7, wherein the first liquid feed pump and the plurality of flow path opening / closing means are controlled so as to perform a buffy coat return step of returning. 9. The blood component collection device includes a centrifuge driving device for rotating the rotor of the centrifuge, and the control unit includes a minimum rotor rotation speed storage function, and a blood source of the blood donor. A rotor rotation speed calculation function for calculating a rotor rotation speed in consideration of a blood flow speed at the time of blood collection of the blood donor using the component concentration, wherein the rotor rotation speed calculated by the rotor rotation speed calculation function is the minimum. If greater than the rotor speed, control the centrifuge drive to rotate the rotor at the calculated rotor speed, if the calculated rotor speed is less than the minimum rotor speed, The blood component collection according to any one of claims 1 to 8, further comprising a function of controlling the centrifugal separator driving device to rotate the rotor at a minimum rotor rotation speed. apparatus. 10. The blood component collection device includes a centrifuge driving device for rotating the rotor of the centrifuge, a hematocrit value input unit or a hematocrit value measurement function, and the control unit includes: , A blood flow velocity calculation function at the time of blood collection of the blood donor, and a minimum rotor rotation number storage function, and the blood flow velocity calculated by the blood flow velocity calculation function is a constant value. If it is larger, the rotor speed calculation function calculates the rotor speed suitable for the hematocrit value using the input or measured hematocrit value, and calculates the blood flow speed calculated by the blood flow speed calculation function. If is less than or equal to a certain value, the rotor speed calculation function calculates the hematocrit using the input or measured hematocrit value. A rotor speed calculated by a predetermined value lower than a rotor speed suitable for the value is calculated, and when the rotor speed calculated by the rotor speed calculation function is larger than the minimum rotor speed, the calculated rotor speed is calculated. Control the centrifugal separator driving device to rotate the rotor by the number, and when the calculated rotor speed is smaller than the minimum rotor speed, centrifugal rotation is performed by rotating the rotor at the minimum rotor speed. The blood component collection device according to any one of claims 1 to 8, further comprising a function of controlling the separator driving device. 11. The hematocrit measurement function is the first line and a third line for anticoagulant injection.
The blood component collection device according to claim 10, which is a hematocrit value measurement sensor provided at a position closer to the blood collection needle than the connection with the line. 12. The blood component collection device according to claim 10, wherein the hematocrit value measurement function is a hematocrit value measurement function using a centrifuge at the time of the first plasma collection step.