JP2012247205A - Blood examination apparatus - Google Patents

Abstract

PROBLEM TO BE SOLVED: To determine an index representing characteristics of blood while considering an aggregate.SOLUTION: A blood examination apparatus 1 comprises a TV camera 3 which images blood passing through a channel section 25, and a computer 7. The computer 7 calculates a total area S_all of a predetermined analysis area A in an image captured by the TV camera 3, calculates a total area S_red that images of red blood cells occupy in the analysis area A, calculates a total area S_agg that an image of an aggregate occupies in the analysis area A, and calculates an index α obtained by dividing the total area S_red with a difference between the total area S_all and the total area S_agg.

Description

  The present invention relates to a blood test apparatus.

  In recent years, with increasing interest in health, blood characteristics (fluidity, oxygen carrying capacity, cohesiveness, etc.) have been attracting attention as health barometers. This blood characteristic is quantified by obtaining an index such as blood cell velocity or blood cell count. There is a hematocrit value as an index representing the characteristics of blood. The hematocrit value is a numerical value indicating the proportion of the volume of blood cells in the blood, and is used for anemia testing. The microhematocrit method is generally used as a method for measuring the hematocrit value. The microhematocrit method is a method in which blood is put into a glass capillary tube, and after the red portion (blood cell component) and the transparent portion of blood are centrifuged, the length of the red portion in the capillary tube is measured. This red part contains white blood cells, but since the number of white blood cells is smaller than the number of red blood cells, the volume of the red part is measured as the volume of red blood cells.

  On the other hand, it is also known to discriminate blood cell types by photographing a blood flow in a state where blood flows in a fine channel without using a centrifugal separation method and analyzing the photographed image. For example, as described in Patent Document 1, a method of determining red blood cells by calculating a hue range of red blood cells and identifying the hue of a captured image is known. Further, as described in Patent Document 2, an edge of a blood cell retention portion (a region where red blood cells, white blood cells, and platelets are retained) is extracted from a captured image, and the total area of the region surrounded by the edge is obtained. It is known.

WO2010 / 092727 JP 2009-276271 A

  However, the method described in Patent Document 1 does not consider aggregates. Aggregates are formed by adhesion of platelets, etc., and there are individual differences in the amount of aggregates. Therefore, in the case of a blood sample with a large amount of aggregates, the aggregates occupy the entire predetermined analysis area in the image. The proportion of increases. Therefore, red blood cells that should have flown into the analysis area are blocked by aggregates and cannot flow into the analysis area, and the number of red blood cells and red blood cells that are less than the true red blood cell count are measured. Will do.

  Therefore, the problem to be solved by the present invention is to obtain an index representing the characteristics of blood in consideration of aggregates.

The invention according to claim 1 for solving the above-mentioned problem is
An imaging means for imaging blood passing through the flow path section;
Analysis region area calculating means for calculating the total area of a predetermined analysis region in the image photographed by the photographing means;
A red blood cell image area calculating means for calculating a total area occupied by an image of red blood cells in the predetermined analysis region;
An aggregate image area calculating means for calculating a total area occupied by an aggregate image in the predetermined analysis region;
An index obtained by dividing the total area calculated by the red blood cell image area calculating unit by the difference between the total area calculated by the analysis region area calculating unit and the total area calculated by the aggregate image area calculating unit Alternatively, the blood test apparatus is characterized by comprising an index calculating means for calculating the reciprocal thereof.

The invention according to claim 2
An imaging means for imaging blood passing through the flow path section;
Analysis region area calculating means for calculating the total area of a predetermined analysis region in the image photographed by the photographing means;
A red blood cell image area calculating means for calculating a total area occupied by an image of red blood cells in the predetermined analysis region;
An aggregate image area calculating means for calculating a total area occupied by an aggregate image in the predetermined analysis region;
An index obtained by dividing the total area calculated by the aggregate image area calculating unit by the difference between the total area calculated by the analysis region area calculating unit and the total area calculated by the red blood cell image area calculating unit Alternatively, the blood test apparatus is characterized by comprising an index calculating means for calculating the reciprocal thereof.

The invention according to claim 3
An imaging means for imaging blood passing through the flow path section;
A red blood cell image area calculating means for calculating a total area occupied by an image of red blood cells in a predetermined analysis region in the image photographed by the photographing means;
An aggregate image area calculating means for calculating a total area occupied by an aggregate image in the predetermined analysis region;
An index calculation unit that calculates an index obtained by dividing the total area calculated by the aggregate image area calculation unit by the total area calculated by the red blood cell image area calculation unit or a reciprocal thereof. This is a blood test apparatus.

  According to invention of Claims 1-3, the parameter | index which considered the aggregate in blood can be calculated | required.

  According to the first aspect of the present invention, it is possible to know the ratio of flow components and red blood cells in blood from the obtained index, and the obtained index can be accurately used for anemia testing and the like.

  According to the invention described in claim 2, it is possible to know the ease of blood aggregation, the ratio of aggregates, and the difficulty of blood flow from the obtained index.

  According to the invention described in claim 3, it is possible to know the balance between the ease of blood aggregation and the ease of flow from the obtained index. In addition, the oxygen carrying capacity of blood can be known.

It is a block diagram which shows the whole structure of a blood test apparatus. It is sectional drawing of a microgate array. It is a top view of the channel part of a microgate array. It is IV-IV sectional drawing. It is a flowchart at the time of calculating | requiring the parameter | index of a blood characteristic. It is the flowchart which showed the flow of the process which calculates the total area of the image of a red blood cell. It is the flowchart which showed the flow of the process which calculates the total area of the image of an aggregate. It is an example of the image | photographed image. It is an example of the analysis area | region in the image | photographed image. It is the image displayed so that the red blood cell in an analysis area | region can be identified. It is the image displayed so that the aggregate in an analysis area | region can be identified. It is the graph which showed the relationship between the parameter | index calculated | required by image analysis in consideration of the aggregate, and the hematocrit value calculated | required by the microhematocrit method. It is the graph which showed the relationship between the parameter | index calculated | required by image analysis, without considering the aggregate, and the hematocrit value calculated | required by the micro hematocrit method.

  EMBODIMENT OF THE INVENTION Below, the form for implementing this invention is demonstrated using drawing. However, the embodiments described below are given various technically preferable limitations for carrying out the present invention, but the scope of the present invention is not limited to the following embodiments and illustrated examples.

  FIG. 1 is a block diagram showing the overall configuration of a blood test apparatus 1 according to the present invention. As shown in this figure, the blood test apparatus 1 guides blood from a supply tank 10 through a microgate array 2 to a discharge tank 11, and obtains an index of blood characteristics from information acquired in the process. .

  The blood test apparatus 1 includes a microgate array (microchannel array) 2, a TV camera 3, a computer 7, a display 8, a supply tank 10, a discharge tank 11, a plurality of solution bottles 13, and so on. In the solution bottles 13,..., Liquids such as physiological saline and physiologically active substances are stored. Blood is stored in the supply tank 10. In the discharge tank 11, blood discharged by a fluid control device 20 described later is stored.

  Blood test apparatus 1 includes fluid control device 20. The fluid control device 20 flows the blood stored in the supply tank 10 into the microgate array 2 at a predetermined pressure, and discharges the blood supplied to the microgate array 2 to the discharge tank 11. Specifically, the fluid control device 20 mixes the blood stored in the supply tank 10 and the liquid stored in the solution bottles 13, and supplies them to the microgate array 2.

  The fluid control device 20 includes a differential pressure control unit 9, a valve 10a, a mixer 12, a pressure pump 15, a pressure reduction pump 16, pressure sensors E1, E2, and the like.

  The mixer 12 is provided between the pressurizing pump 15 and the solution bottles 13. When the mixer 12 selectively opens and closes the flow path from the solution bottles 13 to the pressure pump 15, the liquid in the solution bottles 13 is sent to the pressure pump 15.

  The pressurizing pump 15 is provided between the mixer 12 and the microgate array 2. The pressurizing pump 15 sucks liquid from the solution bottles 13,... Selected by the mixer 12, pressurizes the sucked liquid to the microgate array 2, and sends the liquid to the microgate array 2. When two or more of the solution bottles 13 are selected, the liquids of the selected solution bottles 13 are mixed and supplied to the microgate array 2.

  A valve 10 a is provided in the flow path between the pressurizing pump 15 and the microgate array 2 and is provided at the outlet of the supply tank 10. When the valve 10 a opens the outlet of the supply tank 10, the blood in the supply tank 10 flows out of the supply tank 10, and the blood flowing out of the supply tank 10 is mixed with the liquid flowing from the pressurizing pump 15 to the microgate array 2. Is done.

  The decompression pump 16 is provided between the microgate array 2 and the discharge tank 11. The decompression pump 16 sucks blood mixed with the liquid from the microgate array 2 and discharges it to the discharge tank 11. Thereby, the blood in the microgate array 2 is decompressed.

  The pressure sensor E <b> 1 is provided on the upstream side of the microgate array 2. Specifically, the pressure sensor E <b> 1 is provided between the valve 10 a and the microgate array 2. The pressure sensor E1 detects the pressure P1 on the upstream side of the microgate array 2 and outputs the detected pressure P1 to the differential pressure control unit 9.

  The pressure sensor E <b> 2 is provided on the downstream side of the micro gate array 2. Specifically, the pressure sensor E <b> 2 is provided between the microgate array 2 and the decompression pump 16. The pressure sensor E <b> 2 detects the pressure P <b> 2 on the downstream side of the micro gate array 2 and outputs the detected pressure P <b> 2 to the differential pressure control unit 9.

  The differential pressure control unit 9 controls the pressurization pump 15 and the decompression pump 16. By controlling the pressure pump 15 and the pressure reduction pump 16 by the differential pressure control unit 9, the differential pressure between the upstream side pressure and the downstream side pressure of the microgate array 2 is adjusted and supplied to the microgate array 2. The blood flow rate is adjusted to a predetermined amount. Specifically, the differential pressure control unit 9 feeds back the detected pressures P1, P2 from the pressure sensors E1, E2, and feedback-controls the pressurizing pump 15 and the decompression pump 16 based on the detected pressures P1, P2. The differential pressure between the pressure on the upstream side and the pressure on the downstream side of the microgate array 2 is adjusted to a predetermined value. Note that the differential pressure control unit 9 may be incorporated in the computer 7.

  The sequence control unit 17 performs integrated control of the mixer 12, the differential pressure control unit 9, and the valve 10a. For example, the sequence control unit 17 controls the order of the mixer 12, the differential pressure control unit 9, and the valve 10a. Note that the sequence control unit 17 may be incorporated in the computer 7.

  The configuration of the fluid control device 20 shown in FIG. 1 is an example, and the fluid control device 20 supplies the blood in the supply tank 10 to the microgate array 2, so that the supply tank 10 passes through the microgate array 2. If the flow of blood up to the discharge tank 11 is generated, the configuration of the fluid control device 20 is not limited to that shown in FIG. For example, the decompression pump 16 may be omitted, and the blood in the supply tank 10 may be supplied to the microgate array 2 by the pressurization pump 15 and the valve 10a. Further, the pressurizing pump 15 may be omitted, and the blood in the supply tank 10 may be supplied to the microgate array 2 by the decompression pump 16 and the valve 10a. If the blood stored in the supply tank 10 is mixed with a liquid such as physiological saline or a physiologically active substance, the mixer 12, the solution bottle 13 and the pressurizing pump 15 are omitted (the decompression pump 16 if necessary). May be omitted), a supply pump may be installed instead of the valve 10a, and blood stored in the supply tank 10 may be supplied to the microgate array 2 by the supply pump.

  The micro gate array 2 has a plurality of gates 25a through which the blood supplied from the supply tank 10 circulates (see FIG. 3). Hereinafter, the microgate array 2 will be described in detail with reference to FIG. FIG. 2 is a cross-sectional view of the microgate array 2.

As shown in FIG. 2, the micro gate array 2 includes a base plate 21, silicon single crystal substrates 22, 22, an outer frame 23, a glass flat plate 24, and the like.
The base plate 21 is formed in a substantially flat plate shape, and has an introduction channel 21a and a discharge channel 21b. The introduction channel 21 a and the discharge channel 21 b are formed inside the base plate 21. One end of the introduction channel 21a opens at the peripheral side surface of the base plate 21, the other end of the introduction channel 21a opens at the center of the upper surface of the base plate 21, and the introduction channel 21a extends from the peripheral side surface of the base plate 21 to the base plate. 21 communicates to the center of the upper surface. One end of the introduction channel 21a communicates with the valve 10a through a tube. One end of the discharge channel 21 b opens near the edge of the upper surface of the base plate 21, the other end of the discharge channel 21 b opens at the peripheral side surface of the base plate 21, and the discharge channel 21 b is near the edge of the upper surface of the base plate 21. To the base plate 21 on the peripheral side surface. The other end of the discharge passage 21b communicates with the decompression pump 16 through a tube.

  The silicon single crystal substrates 22 and 22 are arranged on the upper surface of the base plate 21 apart from each other. In the gap 22c between the two silicon single crystal substrates 22 and 22, the other end of the introduction channel 21a of the base plate 21 is opened. In addition, raised portions 22 a are projected on the upper surfaces of the silicon single crystal substrates 22 and 22. The raised portion 22a is perpendicular to the direction in which the silicon single crystal substrates 22 and 22 are juxtaposed (Y direction) and the thickness direction of the silicon single crystal substrates 22 and 22 (vertical direction: Z direction) (X in FIG. 2). Direction: a direction perpendicular to the paper surface of FIG.

  The outer frame 23 is formed in a frame shape so as to surround the periphery of the silicon single crystal substrates 22 and 22. The outer frame 23 is fixed to an edge portion on the upper surface of the base plate 21. The outer frame 23 and the silicon single crystal substrates 22 and 22 are separated from each other, a gap 22d is provided between the outer frame 23 and the silicon single crystal substrates 22 and 22, and the discharge flow path 21b of the base plate 21 is formed in the gap 22d. One end is open.

  The glass flat plate 24 is formed in a flat plate shape. A glass flat plate 24 is fixed to the upper surface of the outer frame 23 so as to close the outer frame 23, and the glass flat plate 24 and the base plate 21 are opposed to each other with a space therebetween. Further, between the lower surface of the glass flat plate 24 and the upper surface of the raised portion 22a, a channel portion 25 of a fine channel group is formed.

  FIG. 3 is a plan view of the flow path portion 25 as viewed from above, and FIG. 4 is a cross-sectional view of the surface along IV-IV shown in FIG. As shown in FIGS. 3 and 4, a plurality of hexagonal bank portions 22b,..., Which are rectifying elements, are projected on the upper surface of the raised portion 22a, and these bank portions 22b,. (Y direction) It is arranged in parallel in the X direction at a predetermined interval in the central portion. The upper surface of the raised portion 22 a is separated from the glass flat plate 24, and the bank portions 22 b,. Thereby, the flow path part 25 is formed on the upper surface of the raised part 22a. The flow path portion 25 is formed between the bank portions 22b,... And arranged in parallel, and is formed closer to the gap 22c (upper side in FIG. 3) than the gates 25a,. The upper terrace 25b, which is a space, and the downstream terrace 25c, which is a space formed on the opposite side (the upper side in FIG. 3) of the gap 22c from the gates 25a,. In the present embodiment, the width t of the gate 25a is formed narrower than the blood cell diameter of red blood cells (about 8 μm). Although not particularly limited, the lengths la, lb, and lc in the width direction (Y direction in the drawing) of the raised portion 22a in the upstream terrace 25b, the gate 25a, and the downstream terrace 25c are all formed to be about 30 μm. Yes.

  In the microgate array 2 having the above configuration, the blood introduced from the supply tank 10 through the introduction flow path 21a passes through the flow path section 25 and is then discharged to the discharge tank 11 through the discharge flow path 21b. It becomes. More specifically, blood cells, for example, red blood cells, in the blood flowing through the flow path section 25 first pass through the upstream terrace 25b, pass through the gate 25a while being deformed, and finally pass through the downstream terrace 25c.

  As shown in FIG. 1, a TV camera 3 as an imaging unit images a blood flow in the microgate array 2. The TV camera 3 is installed opposite to the glass flat plate 24 in the microgate array 2 and photographs the blood flowing through the flow path portion 25 over the glass flat plate 24. The blood image obtained by the TV camera 3 is output to the computer 7 and displayed on the display 8. The TV camera 3 is a digital CCD camera, for example, and is a camera capable of shooting a moving image. More specifically, the TV camera 3 is a high-speed camera having a resolution sufficient for photographing a blood flow. If the TV camera 3 is a high-speed camera, the blood cell shape in the captured image can be recognized even if the blood flow is fast. Note that the TV camera 3 may be a camera that shoots a still image. In that case, the exposure time during shooting is shortened, the shutter speed is increased, or shooting is performed in a dark place with a short flash. Further, when the TV camera 3 is a low-speed moving camera with a small number of frames per unit time, the blood flow is slowed down.

The computer 7 includes a CPU, a RAM, a ROM, a storage medium (for example, a magnetic storage medium, a semiconductor storage medium, etc.), and the like, and performs arithmetic processing according to a program 7a recorded in the ROM or the storage medium. Specifically, the computer 7 analyzes the blood image output from the TV camera 3 according to the program 7a to obtain blood characteristics.
The display 8 displays blood images output from the TV camera 3, blood characteristics obtained by the computer 7, and the like.

Next, the operation of blood test apparatus 1 will be described with reference to FIG.
FIG. 5 is a flowchart showing the operation sequence of the blood test apparatus 1 when obtaining the blood characteristic index.

  As shown in this figure, blood is flowed to the microgate array 2 by the fluid control device 20 (step S1). Specifically, first, blood to be measured is poured into the supply tank 10, and physiological saline or the like is added to the solution bottle 13 as necessary. The sequence control unit 17 controls the differential pressure control unit 9 so that the differential pressure control unit 9 operates the pressurization pump 15 and the decompression pump 16, and the detected pressures P1 and P2 of the pressure sensors E1 and E2 are set. Based on this, the pressure pump 15 and the pressure reducing pump 16 are feedback-controlled. As a result, a predetermined differential pressure is applied to the microgate array 2. Further, when the sequence controller 17 operates the mixer 12 and the valve 10 a, the blood in the supply tank 10 flows to the microgate array 2 due to the differential pressure applied to the microgate array 2.

  When blood is supplied to the microgate array 2 and the blood is passing through the flow path portion 25, the TV camera 3 images the blood in the flow path portion 25 (step S2). The TV camera 3 outputs the taken blood image to the computer 7, and the computer 7 inputs the blood image and causes the display 8 to display the blood image. FIG. 8 shows an example of a blood image taken in the process of step S2. The imaging timing may be any timing as long as blood has flowed into the flow path section 25. Alternatively, the TV camera 3 may take an image of the blood in the flow channel 25 in a state where the blood flow is stopped by the fluid control device 20 after the blood flow is generated in the flow channel 25.

  Next, as shown in FIG. 5, the computer 7 extracts a predetermined analysis region A from the blood image photographed in the process of step S2 (step S3). Specifically, when a moving image is shot in step S2, the computer 7 extracts the analysis area A from predetermined frames in the moving image. When a still image is shot in step S2, the computer 7 The analysis area A is extracted from the still image. The position of the analysis region A may be upstream of the image of the gates 25a,... Or may be downstream of the image of the gates 25a,. FIG. 9 shows an image in the extracted analysis region A. If the shooting range by the TV camera 3 is the analysis area A, the extraction process in step S3 is omitted. In that case, the analysis area A is the entire image taken by the TV camera 3.

  Next, as shown in FIG. 5, the computer 7 calculates the total area S_all of the extracted analysis region A (step S4). Specifically, the computer 7 counts the number of pixels in the analysis region A, and the counted number of pixels represents the total area S_all of the analysis region A.

  Next, the computer 7 recognizes the image of red blood cells included in the extracted analysis region A, and calculates the total area S_red occupied by the image of red blood cells in the analysis region A (step S5). FIG. 10 shows a red blood cell image of the extracted image in the analysis region A that is blacked out.

  Specifically, the computer 7 calculates the total area S_red occupied by the image of red blood cells by performing a process as shown in FIG. First, the computer 7 extracts a predetermined analysis region A from the blood image taken in the process of step S2 (step S51). The image of the analysis area A extracted by the process of step S51 is the same as the image of the analysis area extracted by the process of step S3. Next, the computer 7 binarizes the extracted analysis region A with a predetermined threshold (step S52). The predetermined threshold value divides the gradation value of the red blood cell image from the gradation value of the blood cell type image other than red blood cells. Since red blood cells have lower brightness than aggregates (those with platelets aggregated) or white blood cells, the binarization processing of analysis area A turns the image of red blood cells in analysis area A to a black gradation value (zero). The portion other than red blood cells has a white gradation value (1). After the binarization processing, the computer 7 counts the number of pixels whose gradation value is equal to or smaller than a predetermined threshold value from the extracted analysis region A (step S53). That is, the computer 7 counts the number of pixels having a black gradation value (zero) in the image binarized in the process of step S52. The counted number of pixels represents the total area S_red occupied by the image of red blood cells. Note that the computer 7 may calculate the total area S_red occupied by the red blood cell image by counting the number of pixels in the analysis area A in which the gradation value falls within the red blood cell hue range (red hue range). Good.

  As shown in FIG. 5, after calculating the total area S_red occupied by the image of red blood cells, the computer 7 recognizes the image of the aggregate contained in the extracted analysis region A, and the image of the aggregate in the analysis region A. The total area S_agg occupied by is calculated (step S6). FIG. 11 shows a black image of an aggregate image among the extracted images in the analysis region A. FIG.

  Specifically, the computer 7 calculates the total area S_agg occupied by the aggregate image by performing a process as shown in FIG. First, the computer 7 extracts the analysis region A from the blood image photographed in the process of step S2 (step S61). The image of the analysis area A extracted in the process of step S61 is the same as the image of the analysis area extracted in the process of step S3. Next, the computer 7 applies a Sobel filter in the vertical direction and a Sobel filter in the horizontal direction to the extracted image in the analysis region A, thereby obtaining a blood cell image (red blood cell image, white blood cell image) contained in the analysis region A. And an edge of the blood cell retention portion including the image of the aggregate) (step S62). Then, the computer 7 converts the image of the analysis area A to gray scale and binarizes it with a predetermined threshold (step S63). By the binarization processing, the blood cell staying portion in the analysis region A becomes a white gradation value (1), and the portion other than the blood cell staying portion becomes a black gradation value (zero). Next, the computer 7 expands and contracts the binarized image of the analysis region A by morphological processing, and fills the gaps in the white portion in the analysis region A with white (step S64). The white portion remaining so far is recognized by the computer 7 as a blood cell retention portion.

  Next, the computer 7 determines the white blood cell retention portion as an image of red blood cells, an image of white blood cells, and an image of aggregates (step S65). Specifically, the computer 7 selects an image (or a gradation value of red) with a gradation value equal to or less than a predetermined threshold value from the portion corresponding to the blood retention portion in the analysis region A extracted in step S61. The image of the hue range) is determined as an image of red blood cells. This is because erythrocytes have lower brightness than aggregates and leukocytes. Further, the computer 7 is an image whose gradation value is a predetermined threshold value or more from the portion corresponding to the blood cell retention portion in the analysis region A extracted in step S61 and the unit area of the edge recognized in step S62. An image in which the number of hit pixels is less than a predetermined number is determined as a white blood cell image. This is because white blood cells are brighter than red blood cells and larger than platelets and red blood cells. Further, the computer 7 displays an image whose gradation value is a predetermined threshold value or more from the portion corresponding to the blood cell retention portion in the analysis region A extracted in step S61 and per edge unit area recognized in step S62. An image having a larger number of pixels than the predetermined number is determined as an aggregate image. This is because platelets constituting the aggregate are brighter than red blood cells and smaller than white blood cells and red blood cells.

  Next, the computer 7 counts the number of pixels of the discriminated aggregate image (step S66). The counted number of pixels represents the total area S_agg occupied by the aggregate image.

  For example, Japanese Patent Laid-Open Nos. 10-48120, 10-90163, and 10-275230 can be used to discriminate red blood cells, white blood cells, and aggregate images from the image of the analysis region A. The method described in gazettes etc. may be used.

  As shown in FIG. 5, the computer 7 calculates an index of blood characteristics after calculating the total area S_agg occupied by the aggregate image (step S7). Specifically, as shown in the following equation, the computer 7 calculates an index α obtained by dividing the total area S_red by the difference between the total area S_all and the total area S_agg. The index α represents the ratio of the area occupied by red blood cells in the region where aggregates are excluded from the analysis region A. The ratio of the red blood cells to the flow component can be calculated as the index α without being affected by the presence or amount of aggregates. The computer 7 may calculate an index 1 / α obtained by dividing the reciprocal of the index α, that is, the difference between the total area S_all and the total area S_agg by the total area S_red.

  Further, as shown in the following equation, the computer 7 calculates an index β obtained by dividing the total area S_agg by the difference between the total area S_all and the total area S_red. The index β represents the ratio of the area occupied by the aggregate in the region where red blood cells are excluded from the analysis region A. From the index β, it is possible to know the ease of blood aggregation, the ratio of aggregates, and the difficulty of blood flow. The computer 7 may calculate the index 1 / β obtained by dividing the reciprocal of the index β, that is, the difference between the total area S_all and the total area S_red by the total area S_agg.

  Further, as shown in the following equation, the computer 7 calculates an index γ obtained by dividing the total area S_agg by the total area S_red. The index γ represents the ratio of aggregates to red blood cells. From the index γ, it is possible to know the balance between the ease of blood aggregation and the ease of flow. In addition, the oxygen carrying capacity of blood can be known from the index γ. The computer 7 may calculate the reciprocal of the index γ, that is, the index 1 / γ obtained by dividing the total area S_red by the total area S_agg.

  In step S7, the computer 7 calculates at least one of the indices α, β, γ, 1 / α, 1 / β, 1 / γ. Of course, all of these may be calculated.

  Next, the computer 7 displays the calculated indexes α, β, γ, 1 / α, 1 / β, 1 / γ on the display 8 and calculates the calculated indexes α, β, γ, 1 / α, 1 / γ. β and 1 / γ are stored in the storage medium. Then, one test operation of blood test apparatus 1 is completed.

  As described above, according to the present embodiment, the indices α, β, γ and their reciprocals are obtained from the total area S_agg and the like. Accordingly, it is possible to obtain blood characteristic indexes α, β, γ, 1 / α, 1 / β, 1 / γ in consideration of aggregates. In addition, since the indices α, β, γ, 1 / α, 1 / β, 1 / γ take account of the aggregates, it is possible to perform the imaging in step S2 regardless of the imaging timing.

  For some blood, the index α was calculated using the blood test apparatus 1 described in the above embodiment, and the hematocrit value was measured by the microhematocrit method using a hematocrit centrifuge. Then, as shown in FIG. 12, the measured hematocrit value was plotted on the vertical axis, and the calculated index α was plotted on the horizontal axis. When the correlation coefficient R was obtained by the R-square mean method, the value of the correlation coefficient R was 0.88. Therefore, since the value of the correlation coefficient R is close to 1, it was found that the correlation between the hematocrit value and the index α is high.

  On the other hand, for the same blood, the total area S_red calculated by the blood test apparatus 1 was divided by the total area_all. Then, as shown in FIG. 13, the measured hematocrit value was plotted on the graph with the vertical axis representing S_red / S_all as the horizontal axis. When the correlation coefficient R was obtained by the R-square mean method, the value of the correlation coefficient R was 0.37. Since the correlation coefficient was not close to 1, it was found that the correlation between the hematocrit value and S_red / S_all was low.

1 Blood test apparatus 2 Microgate array 3 TV camera (photographing means)
7 computer (analysis area calculation means, red blood cell image area calculation means, aggregate image area calculation means)
25 Channel section

Claims (3)

An imaging means for imaging blood passing through the flow path section;
Analysis region area calculating means for calculating the total area of a predetermined analysis region in the image photographed by the photographing means;
A red blood cell image area calculating means for calculating a total area occupied by an image of red blood cells in the predetermined analysis region;
An aggregate image area calculating means for calculating a total area occupied by an aggregate image in the predetermined analysis region;
An index obtained by dividing the total area calculated by the red blood cell image area calculating unit by the difference between the total area calculated by the analysis region area calculating unit and the total area calculated by the aggregate image area calculating unit Or an index calculating means for calculating the reciprocal thereof. An imaging means for imaging blood passing through the flow path section;
Analysis region area calculating means for calculating the total area of a predetermined analysis region in the image photographed by the photographing means;
A red blood cell image area calculating means for calculating a total area occupied by an image of red blood cells in the predetermined analysis region;
An aggregate image area calculating means for calculating a total area occupied by an aggregate image in the predetermined analysis region;
An index obtained by dividing the total area calculated by the aggregate image area calculating unit by the difference between the total area calculated by the analysis region area calculating unit and the total area calculated by the red blood cell image area calculating unit Or an index calculating means for calculating the reciprocal thereof. An imaging means for imaging blood passing through the flow path section;
A red blood cell image area calculating means for calculating a total area occupied by an image of red blood cells in a predetermined analysis region in the image photographed by the photographing means;
An aggregate image area calculating means for calculating a total area occupied by an aggregate image in the predetermined analysis region;
An index calculation unit that calculates an index obtained by dividing the total area calculated by the aggregate image area calculation unit by the total area calculated by the red blood cell image area calculation unit or a reciprocal thereof. Blood test device.