BLOOD ANALYZER, BLOOD ANALYZING METHOD, AND PROGRAM FOR BLOOD ANALYZER

Abstract

To provide a blood analysis device that suppresses occurrence of a measurement error regardless of a difference in suspension condition of a blood sample or a state of aggregation of a red blood cell, and can calculate more precisely a hematocrit value or hemoglobin concentration.SOLUTION: A blood analysis device 100, which irradiates an analysis object liquid including at least blood within a translucent tube T with light, and analyses the blood on the light transmitting the tube T, comprises: a light emitting element 2 that emits light so as to cross the tube T relative to a radial direction; a first light reception element 31 that receives the light transmitting the tube T and the analysis object liquid; a second light reception element 32 that receives light reflected or scattered in the tube T or the analysis object liquid toward a light emitting element 2 side; and an analyzer 4 that calculates blood analysis value including at least a hematocrit value or hemoglobin concentration on the basis of an output of the first light reception element 31 and an output of the second light reception element 32.SELECTED DRAWING: Figure 3

Description

[Technical field]

[0001] The present invention relates to a blood analyzer that calculates a hematocrit value or a hemoglobin concentration based on the intensity of light transmitted through blood in a tube. [Background technology]

[0002] For example, in an artificial dialysis system, it is necessary to appropriately manage the flow rate of blood taken from the patient's body and the flow rate of purified blood returned to the patient's body to avoid placing a burden on the patient. For this reason, it is necessary to accurately measure the flow rate of blood flowing through the blood circuit that constitutes the artificial dialysis system.

[0003] In Patent Document 1, a blood analyzer is attached to a tube through which blood flows in order to measure the hematocrit value and hemoglobin concentration required to calculate the blood flow rate. This blood analyzer includes a light emitting unit that emits light across the tube in the radial direction, a light receiving unit that receives the transmitted light that has passed through the tube and blood, and an analysis unit that calculates the transmitted light intensity from, for example, a current value output by the light receiving unit and converts this transmitted light intensity into the hematocrit value and the hemoglobin concentration.

[0004] However, the hematocrit value and hemoglobin concentration measured based only on the transmitted light intensity as described above are affected by the characteristics of the blood itself and its suspension state, resulting in measurement errors between individuals and between blood samples from the same person.

[0005] The inventors of the present application conducted extensive research into such problems and found that measurement errors occur due to the following phenomenon. That is, for example, the size of the area in blood where no blood cells are present differs between cases where red blood cells are aggregated and cases where they are not. The degree of aggregation of red blood cells is also affected by whether the blood is suspended in saline or plasma. As a result, even if there is a blood sample with the same blood concentration (hemoglobin concentration), the size of the area where red blood cells are present and the area where they are not present differs, and the intensity of the detected transmitted light also differs. Therefore, if the hematocrit value or hemoglobin concentration is calculated based only on the intensity of the transmitted light, it will vary greatly due to the effect of the state of aggregation of red blood cells. [Prior art documents] [Patent documents]

[0006] [Patent Document 1] JP 2019-51014 A Summary of the Invention [Problem to be solved by the invention]

[0007] The present invention has been made in consideration of the above-mentioned problems, and has an object to provide a blood analyzer that can suppress the occurrence of measurement errors and more accurately calculate hematocrit value and hemoglobin concentration even if there are differences in the suspension conditions of the blood sample or the aggregation state of red blood cells. [Means for solving the problem]

[0008] In other words, the blood analysis device of the present invention is a blood analysis device that irradiates light onto an analysis liquid containing at least blood in a light-transmitting tube and analyzes the blood based on the light that passes through the tube, and is characterized by comprising a light-emitting element that emits light across the tube in a radial direction, a first light-receiving element that receives light that has passed through the tube and the analysis liquid, a second light-receiving element that receives light reflected or scattered by the tube or the analysis liquid toward the light-emitting element, and an analyzer that calculates blood analysis values ​​including at least hematocrit value or hemoglobin concentration based on the output of the first light-receiving element and the output of the second light-receiving element.

[0009] In addition, the blood analysis method of the present invention is a blood analysis method using a blood analysis device that irradiates light onto an analysis liquid containing at least blood in a light-transmitting tube and analyzes the blood based on the light that passes through the tube, wherein the blood analysis device comprises a light-emitting element that emits light across the tube in a radial direction, a first light-receiving element that receives light that has passed through the tube and the analysis liquid, and a second light-receiving element that receives light reflected or scattered by the tube or the analysis liquid toward the light-emitting element, and calculates blood analysis values ​​including at least hematocrit value or hemoglobin concentration based on the output of the first light-receiving element and the output of the second light-receiving element.

[0010] In such a device, the blood analysis values ​​such as hematocrit value and hemoglobin concentration are calculated using not only the light emitted from the light-emitting element that is not absorbed by and passes through the red blood cells, but also the light that is reflected or scattered by the red blood cells. Therefore, it is thought that measurement errors may occur for the following reasons.

[0011] For example, when red blood cells are agglutinated, the area where no red blood cells are present becomes larger in the area irradiated with light by the light-emitting element, and the amount of transmitted light increases, so that the output of the first light-receiving element becomes larger. On the other hand, the more red blood cells are agglutinated, the less light is reflected or scattered toward the light-emitting element, so that the output of the second light-receiving element becomes smaller.

[0012] Conversely, when the red blood cells are not significantly aggregated and are uniformly dispersed, the intensity of the transmitted light is reduced compared to the state in which the red blood cells are aggregated, and the output of the first light receiving element is reduced. In contrast, the amount of light reflected or scattered toward the light emitting element is increased, and the output of the second light receiving element is increased.

[0013] Therefore, since the output of the first light receiving element and the output of the second light receiving element have inverse change characteristics with respect to the degree of red blood cell agglutination, for example, it is considered that the linear sum of these outputs is likely to reflect only the light absorption in red blood cells. In other words, by using not only the output of the first light receiving element reflecting the intensity of transmitted light, but also the output of the second light receiving element reflecting the intensity of reflected light and scattered light toward the light emitting element, it becomes possible to accurately measure the absorbance corresponding to blood analysis values ​​such as hematocrit value and hemoglobin concentration regardless of the degree of red blood cell agglutination. Therefore, it is considered that the analysis unit can accurately calculate the blood analysis value based on the outputs of the first light receiving element and the second light receiving element.

[0014] For example, in order to obtain an absorbance that accurately reflects the absorption phenomenon occurring in red blood cells regardless of the degree of aggregation of red blood cells or differences in suspension conditions, and thereby accurately calculate the blood analysis value and reduce the variation in measurement error compared to conventional methods, the analyzer only needs to include a first absorbance calculation unit that calculates a first absorbance based on the output of the first light receiving element, a second absorbance calculation unit that calculates a second absorbance based on the output of the second light receiving element, and a conversion unit that converts the linear sum of the first absorbance and the second absorbance into the blood analysis value. In such an analyzer, since a linear sum is used, it is also possible to change the weighting of the output of the first light receiving element and the output of the second light receiving element to adjust the blood analysis value so that it can be accurately calculated.

[0015] A specific example of a simple configuration that eliminates the need for adjustment work and the like while still being able to calculate the blood analysis values ​​such as hematocrit value and hemoglobin concentration more accurately than before is one in which the value conversion unit is configured to convert the sum of the first absorbance and the second absorbance into the blood analysis value.

[0016] The analyzer may include a corrected absorbance calculation unit that calculates a corrected absorbance based on a linear sum of the output of the first light receiving element and the output of the second light receiving element, and a conversion unit that converts the corrected absorbance into the blood analysis value.

[0017] In order to simplify the signal processing from the first light receiving element and the second light receiving element while being able to calculate an accurate blood analysis value, the corrected absorbance calculation unit may be configured to calculate a corrected absorbance based on the sum of the output of the first light receiving element and the output of the second light receiving element.

[0018] For example, in order to ensure measurement accuracy while allowing the first light receiving element and the second light receiving element to be retrofitted to a portion of a tube constituting an artificial dialysis apparatus, and making it difficult for light emitted from a light source other than the light emitting element to enter as stray light into the first light receiving element and the second light receiving element, the light emitting element, the first light receiving element, and the second light receiving element may further be provided with a body in which the light emitting element, the first light receiving element, and the second light receiving element are provided, and the body may include a storage groove into which the tube is fitted, an incident light window that allows light emitted from the light emitting element to enter the storage groove, a transmitted light window that is arranged opposite the incident light window and allows light that has passed through the tube and the liquid to be analyzed to enter from the storage groove to the first light receiving element, and a reflected / scattered light window that is arranged alongside the incident light window in the extension direction of the tube and allows light reflected or scattered by the tube or the liquid to be analyzed to enter from the storage groove to the second light receiving element.

[0019] In order to further prevent stray light from entering the tube from outside the body, the incident light window, the transmitted light window, and the reflected scattered light window are formed on either side of the accommodating groove, and the body has the accommodating groove formed on its bottom surface and further includes a recess extending along the extension direction of the accommodating groove.

[0020] For example, in order to achieve the same effect as the blood analysis device of the present invention by adding the second light receiving element to an existing blood analysis device and updating the program, it is sufficient to use a program used in a blood analysis device that irradiates light onto an analysis liquid containing at least blood in a light-transmitting tube and analyzes blood based on the light that has passed through the tube, wherein the blood analysis device comprises a light-emitting element that emits light radially across the tube, a first light-receiving element that receives light that has passed through the tube and the analysis liquid, and a second light-receiving element that receives light reflected or scattered by the tube or the analysis liquid toward the light-emitting element, and the program for the blood analysis device causes a computer to function as an analyzer that calculates blood analysis values ​​including at least hematocrit value or hemoglobin concentration based on the output of the first light-receiving element and the output of the second light-receiving element. Effect of the Invention

[0021] In this way, with the blood analysis device of the present invention, the transmitted light that passes through the tube and the liquid being analyzed is detected by the first light receiving element, and the light reflected or scattered by the tube or the liquid being analyzed is detected by the second light receiving element, and blood analysis values ​​such as hematocrit value and hemoglobin concentration are calculated based on the output of each light receiving element, making it possible to accurately measure blood analysis values ​​even if there are differences in the degree of red blood cell aggregation or suspension conditions. [Brief description of the drawings]

[0022] [Figure 1] FIG. 1 is a schematic diagram showing a blood analyzer used in an artificial dialysis system according to a first embodiment of the present invention. [Diagram 2] FIG. 2 is a schematic diagram showing details of the blood analyzer of the first embodiment. [Diagram 3] FIG. 2 is a functional block diagram of the blood analyzer of the first embodiment. [Figure 4] 13A and 13B show a comparison between the measurement results of blood analysis values ​​using transmitted light and reflected or scattered light by the blood analysis device of the first embodiment and the measurement results of blood analysis values ​​using only transmitted light, reflected light, or scattered light. [Diagram 5] FIG. 11 is a functional block diagram of a blood analyzer according to a second embodiment. DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS

[0023] A blood analyzer 100 according to a first embodiment of the present invention will be described with reference to FIGS. 1 to 4. FIG.

[0024] The blood analyzer 100 of the first embodiment is used in, for example, an artificial dialysis system 200, and is configured to be retrofittable to a tube T that constitutes a part of a blood circulation circuit. As shown in FIG. 1, the artificial dialysis system 200 includes a dialysis section D where blood and dialysis fluid come into contact with each other through a dialysis membrane, an arterial circuit C1 that connects the inlet side of the dialysis section D to the upstream side of the patient's access blood vessel A, and a venous circuit C2 that connects the outlet side of the dialysis section D to the downstream side of the patient's access blood vessel A. The arterial circuit C1 is provided with a pump C11 for circulating blood, an arterial chamber C12 for removing bubbles in the blood, and the like. The venous circuit C2 is also provided with a venous chamber C22 for removing bubbles. In the first embodiment, the blood analyzer 100 is separately attached to the tube T that connects the outlet side of the venous chamber C22 to the access blood vessel A in the venous circuit C2 and through which purified blood flows.

[0025] Blood analyzer 100 is configured to measure blood analysis values ​​including at least hematocrit value or hemoglobin concentration without contacting the blood flowing through tube T or the analysis target liquid in a state where blood is mixed with physiological saline or the like. Specifically, as shown in Figures 2 and 3, blood analyzer 100 is configured to irradiate light from the outside of tube T and detect light that has passed through tube T and the analysis target liquid and light that has been reflected or scattered by tube T or the analysis target liquid. Furthermore, the hematocrit value or hemoglobin concentration is calculated based on each detection result.

[0026] More specifically, the blood analysis device 100 includes a body 1 having a light-emitting element 2, a first light-receiving element 31, and a second light-receiving element 32, and an analyzer 4 that calculates a blood analysis value based on the output of the first light-receiving element 31 and the second light-receiving element 32.

[0027] The light emitting element 2 is, for example, an LED that emits light with a wavelength in the near infrared region, and emits light with a predetermined distribution along the optical axis. That is, the light emitted from the light emitting element 2 is not only emitted on the optical axis, but also in a direction that forms a predetermined angle with respect to the optical axis. In the first embodiment, the optical axis of the light emitting element 2 is configured to be aligned with the radial direction of the tube T.

[0028] The first light receiving element 31 is a photodiode that receives light transmitted through the tube T and the liquid to be analyzed and outputs a current or voltage according to the intensity of the light. In the first embodiment, the first light receiving element 31 is disposed opposite the light emitting element 2 with the tube T interposed therebetween.

[0029] The second light receiving element 32 is a photodiode that receives light reflected or scattered by the tube T or the liquid to be analyzed toward the light emitting element 2 and outputs a current or voltage according to the intensity of the light. In the first embodiment, the first light receiving element 31 and the second light receiving element 32 have approximately the same output characteristics. The second light receiving element 32 is provided on the same side as the light emitting element 2 with respect to the tube T as a reference, and is located at a predetermined distance from the light emitting element 2 along the axial direction of the tube T. In other words, the second light receiving element 32 is configured so that the light emitted from the light emitting element 2 does not directly enter it.

[0030] The body 1 is generally rectangular parallelepiped-shaped as shown in FIG. 2, and includes the light-emitting element 2, the first light-receiving element 31, and the second light-receiving element 32. The body 1 is provided with a generally rectangular parallelepiped recess 12 extending from one end face to the other end face along the longitudinal direction, which is also the axial direction. Furthermore, the bottom surface of the recess 12 is provided with a receiving groove 11 extending straight along the longitudinal direction, similar to the recess 12, and a flexible tube T constituting a part of the blood circuit is fitted into the receiving groove 11. The width and depth of the receiving groove 11 are set to be approximately the same as the outer diameter of the tube T, for example, and the width of the receiving groove 11 is smaller than the width of the recess 12. The light-emitting element 2, the first light-receiving element 31, and the second light-receiving element 32 are provided in the body 1 so that their optical axes intersect with the side surfaces of the receiving groove 11. In addition, three windows are formed on the side surface of the storage groove 11, so that light targeted by the light emitting element 2, the first light receiving element 31, and the second light receiving element 32 can be emitted or received. More specifically, on the side surface of the storage groove 11, there are formed an incident light window W2 that allows the light emitted from the light emitting element 2 to enter the storage groove 11, a transmitted light window W31 that is provided opposite the incident light window W2 and allows the light that has passed through the tube T and the liquid to be analyzed to enter the first light receiving element 31 from the storage groove 11, and a reflected and scattered light window W32 that is provided next to the incident light window W2 in the extending direction of the tube T (the longitudinal direction of the body 1) and allows the light reflected or scattered by the tube T or the liquid to be analyzed to enter the second light receiving element 32 from the storage groove 11. Since the windows are formed in this way, the first light receiving element 31 can detect almost only transmitted light, and the second light receiving element 32 can detect light reflected or scattered toward the light emitting element 2 side.

[0031] Analyzer 4 has its functions realized by a so-called computer equipped with a CPU, memory, A / D converter, D / A converter, and various input / output devices. A program for blood analyzer 100 stored in the memory is executed, and each device cooperates to perform the functions of first absorbance calculation unit 41, second absorbance calculation unit 42, and conversion unit 43 as shown in Fig. 3. Each unit will be described in detail below.

[0032] The first absorbance calculation unit 41 calculates the first absorbance based on the output of the first light receiving element 31. For example, the first absorbance calculation unit 41 calculates the intensity of the transmitted light detected from the current value output from the first light receiving element 31, and calculates the first absorbance from the intensity of the incident light emitted from the light emitting element 2. Here, the intensity of the incident light emitted from the light emitting element 2 may be the intensity detected by the first light receiving element 31 when no blood is flowing in the tube T, or the theoretical intensity of the incident light emitted from the light emitting element 2 may be used.

[0033] The second absorbance calculation unit 42 calculates the second absorbance based on the output of the second light receiving element 32. For example, the second absorbance calculation unit 42 calculates the intensity of light reflected or scattered toward the light emitting element 2 side detected from the current value output from the second light receiving element 32, and calculates the second absorbance from the intensity of the incident light emitted from the light emitting element 2. Here, the intensity of the incident light used in the second absorbance calculation unit 42 is, for example, the same value as that used in the first absorbance calculation unit 41.

[0034] The conversion unit 43 converts the linear sum of the calculated first absorbance and second absorbance into a blood analysis value. In the first embodiment, a combination of the measured values ​​of the first absorbance and the second absorbance when a liquid to be analyzed, for example, whose hematocrit value or hemoglobin concentration is known, is flowing is measured in advance by an experiment. Combinations of the first absorbance and the second absorbance for a plurality of blood analysis values ​​are actually measured, and a relational expression is determined in advance based on the combinations. For example, a weighting coefficient for the first absorbance and a weighting coefficient for the second absorbance are determined by the least squares method or the like from a plurality of combinations of the blood analysis value, the first absorbance, and the second absorbance determined by an experiment. The conversion unit 43 outputs the blood analysis value by substituting the measured first absorbance and second absorbance into a relational expression in which the first absorbance and the second absorbance determined by an experiment are input variables and the blood analysis value is an output variable. The hematocrit value and the hemoglobin concentration output as the blood analysis value may be displayed externally as a numerical value at that time point, or may be displayed as a graph that changes with time. The hematocrit value and the hemoglobin concentration may also be used to control the flow rate and flow speed of blood flowing through the blood circuit in the artificial dialysis system 200.

[0035] Next, a comparison of the results of measuring hemoglobin concentration using only transmitted light as in the conventional method, measuring hemoglobin concentration using only reflected or scattered light, and measuring hemoglobin concentration based on transmitted light and reflected or scattered light using the blood analyzer 100 of the first embodiment will be described with reference to the graph in Fig. 4. Note that actual measurements were performed in two cases: when the hemoglobin concentration was adjusted by diluting with physiological saline, and when the hemoglobin concentration was diluted with plasma.

[0036] When measuring hemoglobin concentration using only transmitted light as in the past, the increase in absorbance of transmitted light decreases as the hemoglobin concentration increases. In particular, in the region of high hemoglobin concentration, it is difficult to obtain the desired linearity using absorbance only from transmitted light, and measurement errors increase at high concentrations due to individual differences in the analyzed liquid.

[0037] Furthermore, the relationship between the absorbance of only reflected or scattered light and the hemoglobin concentration is not a monotonically increasing relationship, particularly when diluted with physiological saline, and large measurement errors occur.

[0038] On the other hand, the blood analyzer 100 of the first embodiment uses a linear sum of the first absorbance calculated based on the transmitted light and the second absorbance calculated based on the reflected or scattered light, thereby making it possible to suppress the variation between individual differences in the measured values ​​over the entire measurement range compared to the case where only the transmitted light is used. In addition, while the linearity is improved, the response characteristics to the hemoglobin concentration are almost unchanged whether the hemoglobin concentration is diluted with physiological saline or plasma.

[0039] In this way, the blood analyzer 100 of the first embodiment can calculate accurate blood analysis values ​​such as hemoglobin concentration and hematocrit value regardless of individual differences in blood or blood dilution conditions. For example, the artificial dialysis system 200 can obtain accurate blood analysis values ​​regardless of the dilution state by the priming solution used during priming, so it becomes possible to control the blood circulation volume, etc., so as to reduce the burden on the patient.

[0040] Furthermore, since the blood analysis device 100 of the first embodiment is configured to be retrofitted to a tube T, it is possible to attach it to, for example, a tube T that constitutes an existing blood circuit, provide accurate hematocrit values ​​and hemoglobin concentrations to the system, and improve its functions.

[0041] Furthermore, since a storage groove 11 into which the tube T is fitted is formed on the bottom surface of the recess 12 formed in the body 1, it is possible to prevent light emitted from, for example, indoor lighting outside the body 1 from entering the first light receiving element 31 or the second light receiving element 32 as stray light, thereby further reducing measurement errors in blood analysis values.

[0042] Next, a blood analyzer 100 according to a second embodiment will be described with reference to FIG.

[0043] The blood analyzer 100 of the second embodiment differs from the first embodiment in the configuration of the analyzer 4. Specifically, the analyzer 4 does not calculate absorbance individually from the output of the first light receiving element 31 and the output of the second light receiving element 32, but includes a corrected absorbance calculation unit 44 that calculates a corrected absorbance based on the linear sum of the output of the first light receiving element 31 and the output of the second light receiving element 32, and a conversion unit 43 that converts the absorbance into a blood analysis value.

[0044] The corrected absorbance calculation unit 44 calculates a corrected intensity equivalent to the linear sum of the intensity of the transmitted light and the intensity of the reflected or scattered light, based on the linear sum of the current value derived from the transmitted light output from the first light receiving element 31 and the current value derived from the reflected or scattered light output from the second light receiving element 32. Furthermore, the corrected absorbance calculation unit 44 calculates a corrected absorbance from the intensity of the incident light emitted from the light emitting element 2 and the corrected intensity.

[0045] Conversion unit 43 converts the corrected absorbance into blood analysis values ​​including hematocrit value, hemoglobin concentration, etc. Here, the relational equation between the corrected absorbance and the blood analysis value may be created based on values ​​obtained by actually measuring multiple types of analysis target liquids each having a known blood analysis value.

[0046] With blood analyzer 100 of the second embodiment, it is possible to calculate blood analysis values ​​with smaller measurement errors than in the past, similar to the first embodiment.

[0047] Other embodiments will now be described.

[0048] In each embodiment, blood analysis values ​​such as hematocrit value and hemoglobin concentration are calculated from the linear sum of the output of the first light receiving element and the second light receiving element or the absorbance, but the blood analysis value may be calculated using, for example, a simple sum. Also, the analyzer may be configured to calculate the blood analysis value, which is an output variable, using the output of the first light receiving element reflecting the intensity of transmitted light and the output of the second light receiving element reflecting the intensity of reflected or scattered light as input variables. That is, the calculation method is not limited to the one described in each embodiment, and various relational expressions using the intensity of transmitted light or the output of the first light receiving element reflecting it, and the intensity of reflected or scattered light or the output of the second light receiving element reflecting it as input variables may be determined experimentally, for example, to calculate the blood analysis value. Also, the absorbance is calculated using a current value as an output, but the absorbance may be calculated using a voltage.

[0049] The shape of the body is also one example, and may be modified in various ways. For example, the optical axes of the light-emitting element and the light-receiving elements are configured to intersect with the side surface of the accommodation groove, but the optical axes may intersect with the bottom surface of the accommodation groove. In this case, the body may include a cover body that covers the accommodation groove with the tube fitted therein, and either the light-emitting element or the first light-receiving element may be provided inside the cover body.

[0050] Although the blood analyzer is used to configure a part of an artificial dialysis system in each embodiment, the blood analyzer according to the present invention may be used for other purposes or systems. For example, the blood analyzer may be provided in a part of a tube that configures a blood donation system to monitor the state of blood being led out of the body during blood donation. Also, the blood analyzer may be provided in a part of a tube that configures a production line for blood products.

[0051] The blood analysis value is not limited to the hematocrit value or the hemoglobin concentration, and may be other values. For example, the analyzer may be configured to calculate various blood indices that can be converted using the hematocrit value or the hemoglobin concentration, or blood indices that can be calculated in relation to the absorbance.

[0052] In addition, various modifications of the embodiments and combinations of parts of each embodiment may be made without departing from the spirit of the present invention. [Explanation of symbols]

[0053] 200... Artificial dialysis system 100...blood analyzer 1. Body 11. Storage groove 12 Recess 2. Light-emitting element 31 First light receiving element 32 Second light receiving element 4...Analyzer 41...First absorbance calculation section 42...Second absorbance calculation section 43...conversion section 44...Corrected absorbance calculation section

Claims

1. A blood analyzer that irradiates light onto an analysis target liquid containing at least blood in a light-transmitting tube and analyzes the blood based on the light transmitted through the tube, comprising: A light emitting element that emits light in a radial direction across the tube; a first light receiving element that receives light transmitted through the tube and the liquid to be analyzed; a second light receiving element that receives light reflected or scattered by the tube or the liquid to be analyzed toward the light emitting element; a body having a receiving groove into which the tube is fitted; an analyzer that calculates a blood analysis value including at least a hematocrit value or a hemoglobin concentration based on an output of the first light receiving element and an output of the second light receiving element, The body, an incident light window provided on one side surface of the accommodation groove to allow light emitted from the light-emitting element to enter the accommodation groove; a light transmission window provided on the other side surface of the storage groove so as to face the light incident window, the light transmitting window allowing the light having passed through the tube and the liquid to be analyzed to be incident from the storage groove to the first light receiving element; a reflected / scattered light window that is arranged on one side of the storage groove in the extension direction of the tube and is arranged next to the incident light window, and that allows light reflected or scattered by the tube or the liquid to be analyzed to enter the second light receiving element from the storage groove; The analyzer comprises: a first absorbance calculation unit that calculates a first absorbance based on an output of the first light receiving element; a second absorbance calculation unit that calculates a second absorbance based on an output of the second light receiving element; a conversion unit that converts a linear sum of the first absorbance and the second absorbance into the blood analysis value, the conversion unit outputs the blood analysis value by substituting the first absorbance obtained by the first absorbance calculation unit and the second absorbance obtained by the second absorbance calculation unit into a relational equation that is determined based on a combination of each blood analysis value, a first absorbance, and a second absorbance obtained by measuring in advance each of a plurality of analysis target liquids whose blood analysis values ​​are known, and that includes a weighting coefficient for the first absorbance and a weighting coefficient for the second absorbance.

2. 2. The blood analyzer according to claim 1, wherein the body has the storage groove formed in a bottom surface thereof and further includes a recess extending along an extension direction of the storage groove.

3. A blood analysis method using a blood analysis device that irradiates light onto an analysis target liquid containing at least blood in a light-transmitting tube and analyzes the blood based on the light transmitted through the tube, the blood analysis device comprising: a light-emitting element that emits light so as to traverse the tube in a radial direction; a first light-receiving element that receives the light that has transmitted through the tube and the analysis target liquid; a second light-receiving element that receives light reflected or scattered by the tube or the analysis target liquid toward the light-emitting element; a body having a receiving groove into which the tube is fitted; an incident light window provided on one side surface of the storage groove, which allows light emitted from the light-emitting element to enter the storage groove; a transmitted light window provided on the other side surface of the storage groove so as to face the incident light window, which allows light that has passed through the tube and the liquid to be analyzed to enter the first light-receiving element from the storage groove; and a reflected / scattered light window provided on one side surface of the storage groove, aligned with the incident light window in the extension direction of the tube, which allows light reflected or scattered by the tube or the liquid to be analyzed to enter the second light-receiving element from the storage groove, Calculating a first absorbance based on an output of the first light receiving element; Calculating a second absorbance based on an output of the second light receiving element; a linear sum of the first absorbance and the second absorbance is converted into a blood analysis value including at least a hematocrit value or a hemoglobin concentration; a blood analysis method in which the blood analysis value is determined based on a combination of each blood analysis value, a first absorbance, and a second absorbance obtained by previously measuring each of a plurality of analysis target liquids whose blood analysis values ​​are known, and the blood analysis value is determined by substituting the calculated first absorbance and second absorbance into a relational equation including a weighting coefficient for the first absorbance and a weighting coefficient for the second absorbance.

4. A program used in a blood analyzer that irradiates light onto a liquid to be analyzed, which contains at least blood, in a light-transmitting tube, and analyzes the blood based on the light that has passed through the tube, the blood analyzer including a light-emitting element that emits light across the tube in a radial direction, a first light-receiving element that receives the light that has passed through the tube and the liquid to be analyzed, a second light-receiving element that receives light that has been reflected or scattered by the tube or the liquid to be analyzed toward the light-emitting element, and a body having a receiving groove into which the tube is fitted. a light receiving element, an incident light window provided on one side surface thereof for allowing light emitted from the light emitting element to enter the storage groove, a transmitted light window provided on the other side surface of the storage groove opposite the incident light window for allowing light that has passed through the tube and the liquid to be analyzed to enter the first light receiving element from the storage groove, and a reflected / scattered light window provided on one side surface of the storage groove aligned with the incident light window in the extension direction of the tube for allowing light reflected or scattered by the tube or the liquid to be analyzed to enter the second light receiving element from the storage groove, a first absorbance based on an output of the first light receiving element, a second absorbance based on an output of the second light receiving element, and a linear sum of the first absorbance and the second absorbance converted into a blood analysis value including at least a hematocrit value or a hemoglobin concentration, the blood analysis value being determined based on a combination of each blood analysis value, the first absorbance, and the second absorbance obtained by measuring each of a plurality of analysis target liquids in advance, the blood analysis value being known, and the first absorbance and the second absorbance being determined based on a weighting coefficient for the first absorbance and a weighting coefficient for the second absorbance, the blood analysis value being determined based on a combination of each blood analysis value, the first absorbance, and the second absorbance obtained in advance, the blood analysis value being known

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