JPH07119686B2 - Flow cell device - Google Patents

Description

DETAILED DESCRIPTION OF THE INVENTION [Industrial field of application] The present invention is based on the scattered light intensity and / or fluorescence from particles when a fluid containing particles is caused to flow through a capillary channel and light is applied to it. The present invention relates to a flow cell device for an optical particle analyzer that performs particle analysis, and further relates to an optical analyzer and an optical particle detector.

[Conventional technology]

Conventionally, in order to measure the number, type, size or shape of particles such as blood cells, a fluid containing particles is caused to flow through a capillary channel, and light is irradiated to the fluid, and the intensity of scattered light from the particles and / or An optical particle analyzer is used which performs cell analysis, particle measurement and the like based on fluorescence. In the field of cell analysis, such an optical particle analyzer is called a flow cytometer. An example of a flow cytometer is Science 150, pages 630 to 631, 1965 (SCI
ENCE, vol, 150, page 630-631, 1965). The flow cell device of the flow cytometer is shown in FIG.
As shown in FIG. 25, it has a narrow, bow-tie-shaped flow path. Only the cell suspension is flowed through the flow channel.
Therefore, flow cell devices are often clogged during use.

One method to overcome the above drawbacks is US Pat. No. 3,873.
It is disclosed in No. 3,204. In the method, a cell suspension (particle-containing fluid) is flown together with a physiological saline solution in such a manner that it is surrounded by a physiological saline solution (sheath fluid). This method is called the sheath flow method. The sheath flow method is widely used as an effective means in cell analyzers.

Another sheath flow method is Review of Scientific Instruments 46-8, pages 1021 to 1024.
Page 1975 (Review of Seientific Instuments Vol.46, N
o.8, page 1021-1024, August 1975). In this method, a flow cell device having two sheath fluid channels is used.

[Problems to be Solved by the Invention]

In the above-mentioned conventional flow cell device, the capillary flow path is formed by a cylindrical glass tube. Therefore, the thickness of the flow cell device is increasing. Furthermore, since the entrance of the glass tube is funnel-shaped to provide a smooth non-turbulent flow in the capillary channel, the capillary channel is long to avoid interference between the objective lens and the glass tube funnel. Has been done. For example, the diameter of the capillary channel is about 30 mm, and generally about 300 × 10 ⁻⁶ m. for that reason,
The longer the capillary flow path, the greater the pressure loss. Therefore, the flow cell device has a large capacity pump,
Glass tubes and pipes with high pressure resistance are required. This makes the flow cell device itself and the optical analyzer using the flow cell larger. Further, since the flow cell device is made of a glass tube, it is difficult to make the flow cell device precisely.

In another sheath flow type flow cell device, the first sheath fluid is flown in the conical first flow path so as to surround the sample fluid, and the second sheath fluid is It is made to flow in the conical second flow path formed around the flow path. Although the flow cell device can make the flow of the sample fluid more stable, it also has the above-mentioned drawbacks.

An object of the present invention is to provide a sheath flow type flow cell device for a particle analyzer, which can reduce the pressure loss in the capillary flow path and thereby make the fluid system low pressure specification of the particle analyzer.

Another object of the present invention is to provide a sheath flow type flow cell device for a particle analyzer, which can be manufactured easily and precisely and thereby stabilize the flow of a sample fluid.

Yet another object is to provide an optical cell analyzer and particle detector whose fluid delivery system has a low pressure specification and which is compact in size.

[Means for Solving the Problems]

An optical particle analyzer sheath flow type flow cell device according to the present invention is connected to a first inlet for a sheath fluid and a capillary channel communicating with the first inlet and forming a linear flow in a downstream direction. At least two first flow paths, an outlet provided at the end of the capillary flow path, a second inlet for sample fluid, and a second communication port that communicates with the first flow path. And a second flow channel whose opening is opened in the same direction as the capillary flow channel so that a part of the first flow channel is left in the thickness direction of the first flow channel. The flow channel is formed so as to have a substantially flat top surface and a rectangular flow channel, and the sample fluid is analyzed by the particle analyzer.

The optical cell analyzer according to the present invention comprises a first pump for delivering a cell suspension, a diluting device for diluting the cell suspension coupled to the first pump, and a diluting device for the diluting device. A staining device for staining the connected cell suspension, a second pump for transporting the sheath fluid, and a flow cell device formed to have a substantially flat top surface and a rectangular flow path A first inlet for the sheath fluid, at least one first channel communicating with the first inlet and forming a linear capillary channel in the downstream direction, and an end portion of the capillary channel. A discharge port provided, a second inlet for cell suspension, and a second inlet that communicate with the second inlet, are contracted in the downstream direction, and are provided in the first channel above and below the opening. A second channel for cell suspension opened so that a part of one channel is left,
A flow cell device having a capillary flow path and a second flow path opening in the same direction, wherein the first inlet is connected to a second pump and the second inlet is connected to a dyeing device. A flow cell device, a light source that emits a light beam, a condenser lens that irradiates the cell suspension in the capillary channel with the light beam, and an objective lens that is arranged on the substantially flat top surface side and collects fluorescence and scattered light from cells. , A half mirror for separating fluorescence and scattered light, a first photodetector for detecting scattered light, a second photodetector for detecting fluorescence, and connected to the first and second photodetectors Signal processing device.

The optical particle detector according to the present invention comprises a carrier device for sending a particle-containing fluid, a pump for carrying a sheath fluid, a flow cell device, a first inlet for sheath fluid, and a first inlet for sheath fluid. At least two first channels that are in communication with each other and that are connected to a capillary channel that forms a linear flow in the downstream direction, an outlet provided at the end of the capillary channel, and a particle-containing fluid first A second inlet communicates with the second inlet to form a linear flow in the downstream direction, and the opening is formed in the first channel in the thickness direction of the first channel. A second flow path for a particle-containing fluid that is opened in the same direction as the capillary flow path so that a part of the flow path is left, and the flow path part has a substantially flat top surface and a rectangular flow path. A flow cell device in which a passage is formed, which is connected to a first inlet pump and a second inlet Is a flow cell device connected to a carrier device, a light source for emitting a light beam, a condenser lens for irradiating the light beam to a particle-containing fluid in a capillary channel, and a condenser lens arranged on a substantially flat top surface of the flow cell device. It has an objective lens that collects scattered light, a photodetector that detects scattered light, and a signal processing device connected to the photodetector.

[Action]

According to the above configuration, if the flow cell is sandwiched between the upper and lower transparent thin plates and has at least two or more sheath liquid flow passages on both sides of the sample liquid flow passage, the objective lens of the optical system is It can be installed on top of the capillary without being disturbed by anything. This means that the focus of the optical system can be provided immediately after the stable sheath flow is formed in the flow cell, and as a result, the length of the capillary tube can be shortened. Moreover, since the length of the capillary tube can be shortened, the pressure loss can be reduced.

〔Example〕

A sheath flow type flow cell device according to the present invention will be described with reference to FIGS. 1 to 19. 1 to 3 show one embodiment of the sheath flow type flow cell device of the present invention, and the top of the flow cell device is omitted to show the inside. The flow cell device 1 is formed in a plate shape whose top surface 2 is substantially flat. Two inlets 3 for the sheath liquid 4 are provided on the lower side of the flow cell device 1, and two flow paths 5 communicate with the two inlets 3, respectively. The flow path 5 contracts and merges in the downstream direction to form one straight capillary flow path 6. The top and bottom sides of the capillary channel 6 are transparent. The channel 5 and the capillary channel 6 have a substantially rectangular cross section. A discharge port 7 is provided at the end of the capillary channel 6.
Is provided. An inlet 8 for the sample fluid 9 for introducing the cell suspension is provided between the two inlets 3 and under the flow cell device. The flow path 10 communicates with the inlet 8 and contracts in the downstream direction. The flow channel 10 also has a substantially rectangular cross section. Channel 10 is sheath fluid channel 5
Is opened in the confluence point 11 and is opened so that a part of the flow path 5 remains above and below the opening 12. The opening 12 faces in the same direction as the direction of the linear capillary channel 6. Coupling portions 13 for sealingly coupling the flow cell device 1 to the optical particle analyzer are provided at the inlets 3, 8 and the outlet 7, respectively.

A sheath fluid 4 such as physiological saline is introduced into the flow cell device 1 from two inlets 3. The sheath fluid 4 is contracted in the flow channel 5 and flows into the linear capillary flow channel 6 in a laminar flow state. The sample fluid 9 is introduced into the flow cell device 1 through the inlet 8. Sample fluid 9 is the flow path
It is contracted in 10 and flows into the confluence 11 of the flow paths 5. Since a part of the flow channel 5 is left above and below the opening 12, the sample fluid 9 is surrounded by the sheath fluid 4 from the vertical direction in addition to the horizontal direction, and the capillary flow in the linear capillary flow channel 6 is increased. It flows along a narrow flow 14 on the center of the cross section of the path 6. Since the narrow stream 14 is laminar, particles carried by the sample fluid 4, eg cells in suspension, flow one by one. Light rays from a light source (not shown) irradiate a thin stream 14 of the sample fluid 9 from the lower side of the flow cell device 1, and scattered light caused by particles in the sample fluid
Alternatively, fluorescence is collected from the objective lens and particle analysis is performed based on scattered light and / or fluorescence. The seal fluid 4 surrounding the sample fluid 9 that has passed through the capillary channel 6 is discharged from the discharge port 7. The same applies to the flow cell device shown in FIG.

Next, the relationship between the wall portion 15 having the opening 12 and the stability of the sample fluid 9 will be described with reference to FIGS. 4 to 13.
4 to 6 show the flow state of the sample fluid 9 when the corner 16 is provided on the wall portion 15, and FIG. 4 shows the flow state when the flow rate of the sample fluid 9 is small. Cage,
5 shows the flow state when the flow rate of the sample fluid 9 is medium, and FIG. 6 shows the flow state when the flow rate of the sample fluid 9 is high. As shown in FIG. 4, the sample fluid 9 flows stably when the flow rate is small. As shown in FIG. 5, when the flow rate is medium, the sample fluid 9 is open.
After flowing out of 12, the width of the flow widens, but it immediately contracts and becomes a stable laminar flow. As shown in FIG. 6, when the flow rate is high, the wake 17 is generated at the corner 16, and the sample fluid 9 does not flow stably. The limit at which the sample fluid flow is a stable laminar flow is called the stability limit. The stability limit must be increased to quickly analyze the sample fluid. 7 to 9 show a modified example of the wall portion 15 for increasing the stability limit. In the embodiment shown in FIG. 7, the wall portion 15 is rounded and there are no corners causing the wake 17, so the stability limit is increased. In the embodiment shown in FIG. 8, the wall portion 15 is rounded, and the chamfering of the chamfered wall portion 15 allows the sheath fluid 4 to easily laminarly flow into the sample fluid 9.
Since it can flow into the upper and lower sides, the stability limit is further increased. In the modification of FIG. 9, a pair of taper projections 18 are provided on the wall portion. The tapered projection guides the sample fluid 9 flowing out of the flow path 10, so that the sample fluid 9 has a flat and stable flow at the opening 12. As a result, the stability limit is further increased. Figures 10 to 13
The figure shows a modification of the protrusion 18. A pair of plate-like protrusions 18 extend from the wall portion 15 in the flow direction of the sample fluid 9. As shown in the drawing, a gap exists above and below the protrusion. Therefore, the flow of the sheath fluid above and below the flow of the sample fluid 9 is improved, the stability limit is further increased, and the flow of the sample fluid is further flattened. A flat stream of sample fluid is suitable for blood cell analysis. Because flat cells such as red blood cells are aligned in the same direction,
Because it will be washed away. In FIG. 13, the symbol L indicates the flow of the protrusion, and the symbol H indicates the height of the gap.
In cell analysis, the gap height is 100-500 μm, ratio L /
H is preferably 5 or more.

17 to 19 are perspective views showing an embodiment of the present invention, in which a base 23 is pre-processed with a sample fluid inlet 8, two sheath liquid inlets 3, a light irradiation space 14, and an outlet 17. ing. On top of that, a glass plate 24 is placed, and a thin plate lower plate 25, an intermediate plate 26, an upper plate 27, and a glass plate 28, which have been previously processed into a predetermined shape by etching or wire electric discharge machining, are placed thereon in the following order. Stack and join. This forms the flow cell of the present invention. Since all the processes used for manufacturing these are chemical or mechanical processes, the manufacturing accuracy is dramatically improved as compared with the conventional glassworking, and there is an effect that variation can be suppressed at the time of mass production. Further, since the surface roughness of the flow path surface can be freely selected, there is also an effect that the capillary portion, which is significantly influenced by the state of the wall surface, can be finished to have a predetermined surface roughness. Here, the laminated glass plates may be configured as follows. That is, the plurality of laminated plates may be made of a glass plate and a synthetic resin plate such as polyimide, and the glass plates and the synthetic resin may be alternately arranged.

The flow cell device of the present invention is not limited to this embodiment,
The same effect can be obtained even if all the members shown in FIG. 17 are made of glass by using glass etching and optically bonded.
The members shown in FIG. 17 may be manufactured by plastic, and the same effect can be obtained by integrally molding the upper plate 27, the intermediate plate 26, and the lower plate 26 and stacking other members.

According to this embodiment including the modification, since the top surface of the flow cell device is made substantially flat, interference between the flow cell device and the objective lens can be avoided, and the focus of the objective lens can be made thin and stable. It is possible to position the flow at a position positively formed by the capillary channel. Therefore, it is not necessary to lengthen the capillary channel as in the flow cell device of the prior art, and the length of the capillary channel of the present invention may be the minimum required length. The greater the length of the capillary flow path, the smaller the pressure loss, since most of the pressure loss in the flor device is caused by the capillary flow path. In fact, the length of the capillary channel of this embodiment may be 2-3 mm, so the pressure loss is 1/1 times that of the prior art.
It is reduced to about 0. This allows the volume of the pump to deliver the sample fluid or sheath fluid to be smaller,
It enables the pressure resistance of the flow system to be reduced, and further allows the optical particle analyzer to be reduced.

FIG. 21 shows an optical cell analyzer according to the present invention.
The optical cell analyzer has a flow system and an optical system.

The flow system comprises a first pump 31 that delivers a cell suspension 44 and a first pump 31.
Diluting device 32 connected to pump 31 for diluting cell suspension 44, dyeing device 33 connected to diluting device 32 for staining cell suspension 44, and second pump for sending sheath fluid 4. 35
And the flow cell device 1. In this embodiment, the flow cell device shown in FIG. 1 with the projection shown in FIG. 10 is used. The two inlets 3 of the flow cell device 1 are connected to the second pump 35, and the inlet 8 is connected to the dyeing device 33. The cell suspension 44 is sent to the inlet 8 of the flow cell device 1 and flows through the capillary flow path 6
It is being run in a laminar flow state. The cells in the cell suspension 44 are aligned in the same direction and flow one by one in the capillary channel 6. The sheath fluid 4 is sent to the inlet 3 of the flow cell device 1 by the second pump 35, surrounds the cell suspension 44 and flows in the capillary channel 6.

The optical system includes a light source 36 that emits a light beam 46, a condenser lens 37 placed between the light source 36 and the flow cell device 1, an objective lens 38 on a substantially flat top surface side of the flow cell device 1, and a half mirror 39. First photodetector 40 and second photodetector 41
And a signal processing device connected to the first and second photodetectors
42 and. The condenser lens 37 irradiates the cell flowing in the capillary channel 6 with the light ray 46, and the objective lens 38 collects the scattered light and fluorescence caused by the cell.
The half mirror 39 separates the scattered light 43 and the fluorescence 47. First
The photodetector 40 detects the scattered light 43 and converts it into an electric signal. The second photodetector 41 detects the fluorescence and converts it into an electric signal. The signal processing device 42 performs cell analysis from the electric signal.

The optical cell analyzer may include a hemolysis device 34 arranged between the staining device 33 and the inlet 8 of the flow cell device 1. In that case, the pipe between the dyeing device 33 and the entrance 8 is closed.

Since the flow cell device 1 can reduce the pressure loss, the components used in the flow system such as the first and second pumps 31 and 35 may have a low pressure specification. Therefore, the optical cell analyzer has a compact size.

FIG. 22 shows an optical particle detector according to the present invention.
The optical particle detector has a flow system and an optical system.

The flow system has a feed device 48 for feeding the particle-containing fluid 8, a pump 35 for feeding the sheath fluid, and the flow cell device 1. In this embodiment, the flow cell arm 1 shown in FIG. 1 with the protrusions shown in FIG. 10 is used. The feed device 48 is connected to the inlet 8 of the flow cell device 1, and the pump 35 is connected to the inlet 3 of the flow cell device 1. The particle-containing fluid 50 is sent to the inlet 8 of the flow cell device 1 and flows in the capillary channel 6 in a laminar flow state. The particles in the fluid 50 are aligned in the same direction and flow one by one in the capillary channel 6. The sheath fluid 4 is sent by the pump 35 to the inlet 3 of the flow cell device, which surrounds the particle-containing fluid and flows in the capillary channel 6.

The optical system includes a light source 36 that emits a light ray 46, and a condenser lens 37 arranged between the light source 36 and the flow cell side 1.
And the objective lens 38 placed on the top side of the flow cell device 1.
And a photodetector 40 and a signal processing device 49 connected to the photodetector 40. The condenser lens 37 irradiates the particle 46 flowing in the capillary channel 6 with the light ray 46, and the objective lens 38 collects the scattered light caused by the particle. The photodetector 40 detects the scattered light 43 and converts it into an electric signal. The signal processor 49 detects the number of particles from the electric signal. If the optical particle detector is used as a dust counter in air, the particle containing fluid 50 may be air and the sheath fluid 4 may be clean air. When the optical particle detector is used as a dust counter in water, the particle-containing fluid may be water and the sheath fluid may be pure water or clean air.

Since the flow cell device 1 can reduce pressure loss,
Components such as 35 used in the flow system may be low pressure specifications. Therefore, the optical particle detector has a compact size.

FIG. 23 shows the optical cell analyzer shown in FIG.
22 shows a modification of the optical particle detector shown in FIG. The flow cell device 1 has the same configuration as that of the embodiment shown in FIG. A pressure control device 51 is provided between the pump 35 and the inlet 3a of the flow cell device 1, and another pressure control device 52 is provided between the pump 35 and the inlet 3b of the flow cell device 1. In the above-described embodiment, the pressure of the sheath fluid flowing into the inlet 3a and the pressure of the sheath fluid flowing into the other inlet 3b are the same. In this embodiment,
The pressure of the sheath fluid flowing into each inlet is adjustable. In FIG. 23, the pressure of the sheath fluid flowing into the inlet 3a is lower than the pressure of the sheath fluid flowing into the other inlet 3b. As a result, the flow 14 of the particle-containing fluid is moved to the sheath liquid side flowing from the inlet 3a.

With this configuration, the position of the flow of the particle-containing fluid in the capillary channel 6 can be adjusted. This feature is useful for optical particle detectors and optical cell analyzers. The reason is that when the position of the light beam deviates from the flow position of the particle-containing fluid for some reason, by adjusting the pressure of the sheath fluid at each inlet, the position of the flow of the particle-containing fluid is adjusted on the light beam. This is because it can be easily located.

〔The invention's effect〕

According to the present invention, the pressure loss of the flow cell can be reduced and the flow stability can be improved.

Further, since the pressure loss can be reduced, the standardization element used in the flow system can be of a low pressure specification, so that the analyzer and the detector can be downsized.

[Brief description of drawings]

FIG. 1 is a schematic perspective view of an embodiment of a sheath flow type flow cell device according to the present invention, in which the top portion is omitted to show the inside. 2 is a sectional side view of the flow cell device taken along the line II-II in FIG. 1, and FIG. 3 is a portion Λ in FIG.
Is an enlarged perspective view of FIG. 4, FIGS. 4 to 6 are schematic plan views showing the flow state in the capillary channel, and FIGS. 7 to 9 are schematic perspective views of the wall portion where the second channel is opened. FIG. 10 is a perspective view of a pair of protrusions provided on the wall portion, FIG. 11 is a plan view of the protrusion, FIG. 12 is a front view of the protrusion, and FIG. 13 is an explanation of the effective length of the protrusion. FIG. 14 is a schematic side view for, and FIG. 14 is a sectional view of another embodiment of the flow cell device according to the present invention.
Figure 15 is a cross-sectional view along the line XIV-XIV, and Figure 15 is the line in Figure 14.
FIG. 16 is a sectional view taken along the line XV-XV, and FIG. 16 is a sectional view of a flow cell device showing another embodiment. FIG. 17 is a perspective view of another embodiment of the flow cell device according to the present invention, which is opened for explaining the structure. FIG. 18 is a perspective view of another embodiment of the flow cell device according to the present invention, FIG. 19 is a perspective view of another embodiment of the flow cell device according to the present invention, and FIG. 20 is a schematic side view of the flow cell device of FIG. FIG. 21 is a schematic perspective view of an optical cell analyzer according to the present invention, FIG. 22 is a schematic perspective view of an optical particle detector according to the present invention, and FIG. 23 is an optical cell analyzer of FIG. 21 is a schematic plan view of a portion of the optical particle detector of FIG. 21, FIG. 24 is a perspective view of a prior art flow cell device,
FIG. 25 is a side view of a conventional optical cell analyzer. 1 ... Flow cell device, 3 ... Sheath liquid inlet, 4 ...
Sheath fluid, 5 ... Sheath channel, 6 ... Capillary channel, 8
…… Sample liquid inlet, 9 …… Sample liquid.

Front Page Continuation (72) Inventor Fujiya Takahata 882 Ige, Katsuta City, Ibaraki Prefecture Naka Factory, Hitachi, Ltd. (56) Reference JP-A-59-102139 (JP, A) Shoukai 61-63145 ( JP, U)

Claims (14)

[Claims] 1. A sheath flow type flow cell device for an optical particle analyzer, comprising a first inlet for sheath fluid, and a capillary channel communicating with the first inlet and forming a linear flow in a downstream direction. At least two first flow paths connected, and a discharge port provided at the end of the capillary flow path,
A second inlet for the sample fluid and a second inlet are communicated with each other, and the opening portion has a portion of the first channel in the thickness direction of the first channel in the first channel. As it is left, and comprising a second flow path opening in the same direction as the capillary flow path,
A flow cell device, characterized in that these flow path portions are formed so as to have a substantially flat top surface and a rectangular flow path, and the sample fluid is analyzed by a particle analyzer. 2. The sheath flow type flow cell device according to claim 1, wherein the wall portion of the second flow path which is open is formed into a round shape. 3. The sheath flow type flow cell device according to claim 2, wherein the wall portion is chamfered. 4. The sheath flow type flow cell device according to claim 2, wherein the flow cell device further comprises a pair of projections for guiding the flow of the sample fluid into the at least two first flow paths. And a flow cell device having a protrusion extending from the wall portion. 5. The sheath flow type flow cell device according to claim 3, wherein the flow cell device further comprises a pair of protrusions for guiding the flow of the sample fluid into the at least two first flow paths. And a flow cell device having a protrusion extending from the wall portion. 6. The sheath flow type flow cell device according to claim 1, wherein the flow cell device is formed by an upper plate and a lower plate, and the upper plate has at least two first flow paths. A part of the second flow path,
A part of the capillary channel is formed, and the lower plate has another portion of the at least one first channel, another portion of the second channel, and the first portion. A flow cell device comprising an inlet, the second inlet, the outlet, and the connecting portion. 7. The sheath flow type flow cell type flow cell device according to claim 1, wherein the flow cell device has a plurality of laminated plates, and when the plurality of plates are stacked on each other, at least A flow cell device characterized in that a predetermined pattern for forming two first channels, the discharge port, and the second channel is formed. 8. The sheath flow type flow cell device according to claim 7, wherein the plurality of laminated plates are made of glass. 9. The sheath flow type flow cell device according to claim 7, wherein the plurality of laminated plates are made of a glass plate and a synthetic resin such as polyimide, and the glass plate and the synthetic resin plate are different from each other. A flow cell device characterized by being arranged alternately. 10. A first pump for delivering a cell suspension, a diluting device coupled to the first pump for diluting the cell suspension, and a cell suspension connected to the diluting device. A dyeing device for dyeing a turbid liquid, a second pump for transporting a sheath fluid, and a flow cell device, which is formed to have a substantially flat top surface and a rectangular flow path. A first inlet, at least one first channel communicating with the first inlet and forming a linear capillary channel in the downstream direction, and an outlet provided at the end of the capillary channel And a second inlet for cell suspension, which is in communication with the second inlet, is contracted in the downstream direction, and has a first channel above and below the opening in the first channel. The second channel for cell suspension opened so that a part is left, and the second channel opened in the same direction as the capillary channel. A flow cell device having a flow path, the first inlet is connected to a second pump, the second inlet is connected to the dyeing device, a flow cell device, a light source for emitting a light beam, a light beam Condenser lens for irradiating the cell suspension in the capillary channel, an objective lens arranged on the substantially flat top surface side for collecting fluorescence and scattered light from cells, and a half mirror for separating fluorescence and scattered light When,
Optical type having a first photodetector for detecting scattered light, a second photodetector for detecting fluorescence, and a signal processing device connected to the first and second photodetectors Cell analyzer. 11. The optical cell analyzer according to claim 10, wherein the analyzer further comprises a hemolysis device arranged between the staining device and the second inlet of the flow cell device. An optical cell analyzer characterized by: 12. The optical cell analyzer according to claim 10, wherein the first inlet comprises two inlets, and two pressure control devices are respectively connected to the two inlets. Characteristic optical cell analyzer. 13. A delivery device for delivering a particle-containing fluid,
A pump for conveying a sheath fluid, a flow cell device, and a first inlet for sheath fluid, and at least a capillary channel communicating with the first inlet and forming a linear flow in the downstream direction. Two first channels, an outlet provided at the end of the capillary channel, a second inlet for particle-containing fluid, and a second linear inlet that communicates with each other and have a linear flow in the downstream direction. Is formed, and the opening is opened in the same direction as the capillary channel so that a part of the first channel is left in the thickness direction of the first channel in the first channel. A flow cell device having a second flow path for a particle-containing fluid, wherein the flow path portion has a substantially flat top surface and a rectangular flow path, the first inlet being connected to a pump. , A flow cell device having a second entrance connected to a carrier device, a light source for emitting a light beam, and a light beam A condenser lens for irradiating a particle-containing fluid in a capillary channel, an objective lens arranged on a substantially flat top surface of the flow cell device for collecting scattered light from particles, and a photodetector for detecting scattered light, An optical particle detector having a signal processor connected to the photodetector. 14. The optical particle detector according to claim 13, wherein the first inlet is composed of two inlets, and two pressure control devices are respectively connected to the two inlets. Characteristic optical particle detector.