KR102168852B1 - Apparatus for Measuring hemoglobin in blood - Google Patents

Abstract

The present invention relates to a device for measuring hemoglobin in blood. The device comprises: a light irradiation unit emitting incident light of a first wavelength, incident light of a second wavelength, and incident light of a third wavelength different from each other; a cuvette receiving unit configured to receive a cuvette for a whole blood sample; a light detection unit detecting optical density by the incident light of the first to third wavelengths passing the cuvette of the cuvette receiving unit; a control unit controlling the light irradiation unit and cuvette receiving unit so that the incident light from the first wavelength to third wavelength is sequentially irradiated to a sample of the cuvette and controlling the optical density by the incident light of the third wavelength to be measured several times at predetermined time intervals; and a calculation unit estimating convergence values of the optical density from the first wavelength to the third wavelength from a change rate of the optical density of the third wavelength measured several times and determining the concentration of hemoglobin of whole blood from the estimated convergence values of the optical density from the first wavelength to the third wavelength.

Description

Apparatus for Measuring hemoglobin in blood}

The present invention relates to an apparatus for measuring the concentration of hemoglobin in blood to check for anemia and the like.

Hemoglobin is an iron-containing protein present in red blood cells and is the main transport vehicle of oxygen in the blood. Oxygen bound to hemoglobin is released into plasma and absorbed into tissues under certain conditions. One molecule of hemoglobin binds to four oxygen molecules, and the degree of oxygen binding of hemoglobin at a specific point in time for its total binding capacity is called saturation. The amount of oxygen bound to hemoglobin at a specific point in time is mainly determined by the oxygen partial pressure in the environment in which hemoglobin contacts. In general, oxygen saturation is high in arterial blood and low in venous blood. The amount of hemoglobin is expressed as the average hemoglobin concentration per a certain volume of red blood cells, and the average red blood cell volume, average red blood cell hemoglobin, and average red blood cell hemoglobin concentration are called the red blood cell index.

Anemia can be caused by a variety of causes. Since the erythrocyte indexes are different for each diagnosis, it is very important to measure the amount of hemoglobin in the differential diagnosis of anemia. In addition, hemoglobin content is a sensitive indicator of iron deficiency. These indicators can be used to diagnose diseases due to iron deficiency or to monitor the efficacy of intravenous iron therapy.

To measure the hemoglobin concentration of whole blood, capillary blood is collected and used mainly from the fingertips and heels due to its simplicity.These capillaries are combined with oxygen, so they may not uniformly represent the hemoglobin concentration of the whole blood. Therefore, as time elapses after capillary blood is collected, oxygen in the blood may be separated and become close to venous blood.Therefore, hemoglobin concentration can be measured in capillary blood 30 seconds after collection, but this may delay the measurement time too much. do.

Therefore, in order to obtain an accurate value within a short time, generally, blood is collected several times and measured, or venous blood is collected and used. However, collection of venous blood requires expert help, and multiple measurements may cause a lot of inconvenience to the user, leading to avoidance of measurement. In particular, in the case of a point of care blood hemoglobin measurement device, venous blood collection is not It is important to obtain accurate results from capillaries such as the fingertips, as this is not practically possible.

The present invention provides a blood hemoglobin measuring device capable of obtaining a rapid and accurate hemoglobin concentration value from capillary blood.

The present invention is a blood hemoglobin concentration measuring apparatus, a light irradiation unit for emitting three different first wavelength incident light, second wavelength incident light, and third wavelength incident light, a cuvette receiving unit configured to receive a cuvette for a whole blood sample, and a cuvette receiving unit A light detection unit that detects absorbance by incident light of a first wavelength to a third wavelength that has passed through a negative cuvette, and a light irradiation unit and a cuvette receiving unit so that incident light of the first wavelength to the third wavelength is sequentially irradiated to the sample of the cuvette. Controlling, but controlling the absorbance by the third wavelength incident light to be measured several times at predetermined time intervals, and the convergence value of the absorbance of the first wavelength to the absorbance of the third wavelength from the rate of change of the absorbance of the third wavelength measured several times. And a calculation unit that estimates and determines a blood hemoglobin concentration of whole blood from convergence values of the absorbance of the first wavelength to the third wavelength.

The apparatus for measuring hemoglobin in blood according to the present invention uses a model that measures the hemoglobin concentration by using the absorbance estimate value after a predetermined period of time has elapsed by using absorbance measured by light sources of three wavelengths for the collected blood. Therefore, it is possible to obtain the same concentration of hemoglobin as measured in venous blood at a time point in which much time has not elapsed after capillary blood is collected.

1 is a block diagram of an apparatus for measuring hemoglobin in blood according to an embodiment of the present invention.
FIG. 2 is a diagram illustrating an implementation example of an apparatus for measuring hemoglobin in blood according to an embodiment of the present invention. 3 is a diagram showing a graph of the molar absorption coefficient of Moaveni.
4 is a view showing an implementation example of a cuvette holder according to an embodiment of the present invention.
5 is a flowchart illustrating an operation of measuring hemoglobin in blood according to an embodiment of the present invention.
6 is a flowchart illustrating a process of calculating hemoglobin in blood according to an embodiment of the present invention.

The foregoing and additional aspects are embodied through embodiments described with reference to the accompanying drawings. It is understood that the constituent elements of each embodiment can be variously combined within the embodiment unless otherwise stated or contradictory to each other. Each block in the block diagram may represent a physical part in some cases, but may be a part of a function of one physical part or a logical representation of a function across a plurality of physical parts in another case. Sometimes the entity of a block or part of it can be a set of program instructions. All or part of these blocks may be implemented by hardware, software, or a combination thereof.

1 is a block diagram of an apparatus for measuring hemoglobin in blood according to an embodiment of the present invention, FIG. 2 is a diagram showing an implementation example of an apparatus for measuring hemoglobin in blood according to an embodiment of the present invention, and FIG. 3 is (Moaveni) is a diagram showing a graph of the molar absorption coefficient.

The light source of the light irradiation unit 110 of the blood hemoglobin measuring apparatus 100 of the present application is a first wavelength in the range of about 400 to 420 nm, a second wavelength in the range of about 800 to 830 nm, and a third wavelength in the range of about 520 to 550 nm. Emits incident light. As a light source, a light source emitting light of a specific wavelength may be used, or continuous light emitting a wavelength band over a wide area may be used together with a filter. According to an aspect, a light source emitting a specific wavelength, for example, a light emitting diode (LED) or a laser diode is used, but is not limited thereto. When continuous light is used, a filter for a specific wavelength is used together.

As used herein, light of each wavelength is emitted from a single light source that is integrally formed or, as shown in FIG. 1, three separate light sources 110-1, 110-2, and each of which emit light of each wavelength. 110-3). According to an aspect of the present disclosure, light of one type of wavelength is emitted from each of the three light sources 110-1, 110-2, and 110-3. While the light of one wavelength is emitted, the light of the other wavelength is turned off, and the light of the one wavelength is irradiated for a predetermined time to collect data of the light transmitted through the blood sample, and then converted to the off state. Then, light of different wavelengths is irradiated in the same way. In this case, the data read by the light detection unit is not used until the brightness of light irradiated from the light source is stabilized, and it is preferable that the light is not incident on the sample, which is controlled by the controller 160 of the present application to be described later.

The wavelengths irradiated from the light sources 110-1, 110-2, 110-3 of the light irradiation unit 110 used herein are the same for both oxidized hemoglobin (HbO ₂ ) and reduced hemoglobin (Hb) included in whole blood. / A wavelength that exhibits similar absorbance is used.

Referring to Figure 3, it can be seen that the same/similar absorbances are shown for both oxidized hemoglobin (HbO ₂ ) and reduced hemoglobin (Hb) contained in whole blood in a range of wavelengths of approximately 410 nm, 530 nm and 830 nm. Accordingly, according to an aspect of the present disclosure, the first wavelength may be in the range of 400 to 420 nm, the second wavelength may be in the range of 800 to 830 nm, and the third wavelength may be in the range of 520 to 550 nm.

That is, in the case of the first wavelength, a wavelength exhibiting strong absorbance for both oxidized and reduced hemoglobin is used, and in the case of the second wavelength, it is lower than the absorbance by the first wavelength, and may be used as a background value. And, in the case of the third wavelength, it can be used as a target for estimating the coefficient of change in which it is easy to measure the rate of change over time. When outside the above range, the absorption wavelength bands of oxidized and reduced hemoglobin do not coincide, so it may be difficult to accurately measure the concentration of hemoglobin.

The blood hemoglobin measuring apparatus 100 of the present application may be integrally provided in the housing 1 in an arrangement as described in FIG. 2 in one embodiment, and the housing 1 of the blood hemoglobin measuring apparatus 100 of the present application There is formed a cuvette receiving portion 30, which is an insertion space concave from one side, so that the micro cuvette 200 can be accommodated in the cuvette receiving portion 30. The micro cuvette 200 includes a sample injection unit 210, whole blood used for measuring hemoglobin concentration is introduced into the sample injection unit 210, and the sample injection unit 210 of the micro cuvette 200 is a light irradiation unit ( It is composed of an optical material through which the light source irradiated from 110) can pass, and is disposed in the blood hemoglobin measuring apparatus 100 of the present application so that the light can be irradiated and passed. The micro cuvette 200 is mounted on the cuvette holder 120 to be described later when used in the blood hemoglobin measuring apparatus 100 of the present application.

Micro cuvette 200 that can be used herein is disposable, and is an integral type composed of a body and a space formed in the body, that is, the space is formed by the inner surfaces of two flat plates forming the body facing each other, and a part of the space The sample injection part 210 is located, a capillary inlet connected to the space is formed at an end of the body, and an inlet port connected to the space is formed at an opposite end of the body where the capillary inlet is not formed. Accordingly, it is possible to directly collect blood from the fingertip through the capillary inlet, or to inject the blood into the inlet using a pipette, and then perform optical analysis. Cuvettes of this type are produced, for example, by injection molding and can be made of transparent polymeric materials.

4 is a view showing an example implementation of the cuvette holder according to the present invention.

According to another embodiment, a convex lens 121 may be provided under the cuvette holder 120. The convex lens 121 performs a function of collecting light that has passed through the whole blood sample of the cuvette 200 after being radiated from the light irradiation unit 110.

In this case, a first slit of the light irradiation unit 110 may be provided, and a second slit may be provided at a lower end of the convex lens 121. Accordingly, the incident light output from the light irradiation unit 100 passes through the first slit and then passes through the whole blood sample of the sample injection unit 210 of the cuvette 200 on the cuvette holder 120. Incident light passing through the whole blood sample of the sample injection unit 210 is collected by the convex lens 121 and passes through the second slit to be detected by the light detection unit 130. Here, the first slit may have a diameter of about 2 mm, and the second slit may have a diameter of about 3 mm. Accordingly, since incident light emitted from the light irradiation unit 110 does not spread and reaches the light detection unit 130, the absorbance measurement performance may be improved.

The micro cuvette 200 of the present application may be mounted and used in a cuvette holder 120 that can accommodate it, and in this case, the cuvette holder 120 equipped with the micro cuvette 200 as shown in FIG. 2 accommodates the cuvette. It is accommodated in the unit 30. The cuvette holder 120 introduces the sample injection part 210 of the micro cuvette 200 to an accurate position with respect to the light source, and facilitates the entry and exit of the cuvette into the blood hemoglobin measuring apparatus 100. In addition, by shielding the entry of an external light source into the cuvette, the measurement accuracy is ensured, and the cuvette is at an appropriate speed for the blood hemoglobin measuring device 100, that is, equal to or greater than the capillary force acting on the blood sample of the cuvette sample injection unit 210 It is inserted so that a small force is applied to prevent the sample on the cuvette from being pulled in one direction due to sudden mounting.

The blood hemoglobin measuring apparatus 100 of the present application includes a detection unit 130 for detecting absorbance of incident light of a first wavelength, absorbance of incident light of a second wavelength, and absorbance of incident light of a third wavelength that have passed through a blood sample. Light of each wavelength irradiated by the light sources 110-1, 110-2, 110-3 of the light irradiation unit 110 passes through the blood, and the passed light is detected by the detection unit 130. For light transmitted through the sample, a first absorbance is measured for light of a first wavelength, a second absorbance is measured for light of a second wavelength, and a third absorbance is measured for light of a third wavelength. 130). Here, the absorbance may be expressed as a common log value of the molar absorption coefficient of Moaveni shown in FIG. 3.

According to an embodiment of the present invention, under the control of the controller 160 to be described later, the third absorbance is measured a predetermined number of times or more at predetermined intervals within a predetermined time range and processed by the calculation unit 140 to be described later.

According to the present invention, the above-described light irradiation unit 110, cuvette holder 120, and detection unit 130 are mechanically variously implemented to measure the sequential absorbance of light of the first wavelength, the second wavelength, and the third wavelength. It can be implemented with examples.

As an example, the light sources 110-1, 110-2, 110-3 of the light irradiation unit 110 are sequentially fixed to a predetermined area on one side of the housing 1 of the blood hemoglobin measuring apparatus 100 The detection unit 130 may be attached to a lower portion of the cuvette holder 120 where the sample injection unit 210 is positioned and may be moved together with the cuvette holder 120. Accordingly, according to the control signal of the control unit 160, the sample injection unit 210 may be configured to transmit the light sources 110-1, 110-2, and 110-3 to each of the light sources 110-1, 110-2, and 110-3. 1, 110-2, 110-3) The movement of the cuvette holder 120 may be controlled to be positioned at each light irradiation position.

In another embodiment, the detection unit 130 is at the position of the sample injection unit 210 in a state in which the cuvette holder 120 is accommodated into the housing 1 on the other side facing the inner side of the housing 1 It may be fixedly disposed, and the light sources 110-1, 110-2, 110-3 of the light irradiation unit 110 may be sequentially disposed on one side of the interior of the housing 1 but may be implemented in a movable form. . For example, the light sources 110-1, 110-2, and 110-3 may be rotated. Accordingly, according to the control signal of the control unit 160, at the time when each of the light sources 110-1, 110-2, and 110-3 sequentially emit incident light, the sample injection unit 210 (110-1, 110-2, 110-3) Movement of the light sources 110-1, 110-2, and 110-3 may be controlled to be positioned at respective light irradiation positions.

The blood hemoglobin measurement apparatus 100 includes a calculation unit 140. The first to third absorbance measurement results according to the present application are processed to determine the concentration of hemoglobin in whole blood, and the processing for this is performed by a predetermined algorithm to calculate the concentration of hemoglobin. The detailed configuration and operation of the calculation unit 140 will be described later with reference to FIG. 6.

In an embodiment, the algorithm may be integrated into the blood hemoglobin measuring apparatus 100 as a program to detect absorbance and then convert it into hemoglobin concentration and output the measured value to be displayed on the display unit 10 as shown in FIG. 2.

Accordingly, the blood hemoglobin measuring apparatus 100 of the present application may further include an output generator 150 that generates and outputs the state or detection result of the blood hemoglobin measuring apparatus 100.

The output generator 150 outputs the hemoglobin concentration and state to a communication port (not shown) for exchanging data with the display unit 10 shown in FIG. 2 or an electronic device connected to the blood hemoglobin measuring apparatus 100.

Here, on the display 10, for example, the state/status of the hemoglobin measurement progress, the state of the hemoglobin measuring apparatus 100 in the blood, the absorbance, and the concentration of hemoglobin are displayed. Further, the electronic equipment is an electronic equipment for storage of hemoglobin concentration data and data analysis for providing information necessary for disease diagnosis, and includes, for example, a computer, a printer, a cell phone, a smartphone, etc., but is not limited thereto.

The blood hemoglobin measurement apparatus 100 of the present application also includes a control unit 160 to control the above-described components to control the blood hemoglobin measurement, and a detailed description thereof will be described later with reference to FIG. 5.

The apparatus for measuring hemoglobin in blood of the present application 100 may be integrally provided in the housing 1 in an arrangement as described in FIG. 2 as an embodiment, but in another embodiment, the calculation unit 140 or the control unit of the present application 160 may be configured to be located integrally or separately from other components of the apparatus 100 for measuring blood hemoglobin in the present application. In addition, the calculation unit 140 and the control unit 160 may be integrally configured.

5 is a flowchart illustrating an operation of measuring hemoglobin in blood according to an embodiment of the present invention.

5, the control unit 160 drives the light irradiation unit 110, the cuvette holder 120 and the measurement unit 130 as the micro cuvette 200 supplied with blood is mounted on the cuvette holder 120 By controlling the absorbance measurement operation is started (S210).

The control unit 160 drives the first light source 110-1 to adjust the incident light of the first wavelength to be irradiated to the sample injection unit 210, and then drives the measurement unit 130 to measure the first absorbance ( S220). Thereafter, the second light source 110-2 is driven to adjust the incident light of the first wavelength to be irradiated to the sample injection unit 210, and then the measurement unit 130 is driven to measure the second absorbance (S230). . At this time, before the light of each wavelength is irradiated to the sample, the amount of light of each wavelength is stabilized, and then the irradiation is adjusted. It goes without saying that the order of the first wavelength and the second wavelength may be changed.

Next, the control unit 160 drives the third light source 110-3 to adjust the incident light of the third wavelength to be irradiated to the sample injection unit 210, and then drives the measurement unit 130 to adjust the third absorbance. It measures (S220). According to an aspect of the present application, the third absorbance measurement may be repeatedly performed within a predetermined time, for example, 10 seconds. Since the third absorbance gradually decreases as time elapses and converges to a predetermined value, a difference value, that is, a decrease value, between the measured third absorbances according to the repetition is also gradually decreased. Accordingly, in the present invention, when the decrease value becomes less than a predetermined threshold, it is determined that the third absorbance has reached a stable value, and the measurement is stopped.

Accordingly, the control unit 160 repeats the third absorbance measurement in step S240 until the reduction value becomes less than or equal to a predetermined threshold (S250). However, according to an embodiment, even if the reduction value does not become less than the predetermined threshold value, when a predetermined time, for example, 10 seconds elapses (S260), the third absorbance measurement is stopped. This is because the blood hemoglobin measuring apparatus 100 of the present application aims to quickly measure hemoglobin.

Then, the control unit 160 inputs the first absorbance measurement value, the second absorbance measurement value, and the plurality of third absorbance measurements into the calculation unit 140 to be described later to calculate the hemoglobin concentration in the blood (S270). This will be described later with reference to FIG. 6.

Then, the control unit 160 outputs the blood hemoglobin concentration calculated by the calculation unit 140 (S280).

6 is a flowchart illustrating a process of calculating hemoglobin in blood according to an embodiment of the present invention.

Referring to FIG. 6, the third absorbance estimation unit 141 of the calculation unit 140 estimates a third absorbance convergence value X ₃ (S271 ). That is, the third absorbance estimating unit 141 is a difference value (x _{3_n} -x _{3_n-} ) between the plurality of third absorbance measurement values (x _{1_1} , x _{1_2} ,.., x _{1_n} ) measured by the measurement unit 130. ₁ ) The third absorbance convergence value (X ₃ ) is estimated according to the rate of change over time, that is, the decrease rate of the third absorbance measurement value (S271).

Then, the third absorbance estimating unit 141 is at the point when the third absorbance convergence value (X ₃ ) and the decrease value (x _{3_n} -x _{3_n-1} ) become less than a predetermined threshold value, as shown in Equation 1 below. A third coefficient of change W ₃ that satisfies the following <Equation 1> between the third stable absorbance value (x _{3_n} ) is estimated (S273).

Then, the third absorbance estimating unit 141 of the calculating unit 140 transmits the calculated third coefficient of change W ₃ to the first absorbance estimating unit 142 and the second absorbance estimating unit 143.

Each of the first absorbance estimating unit 142 and the second absorbance estimating unit 143 is a first absorbance measured from the first absorbance measurement value (x ₁ ) and the second absorbance measurement value (x ₂ ) according to the following <Equation 2>. The convergence value (X ₁ ) and the second absorbance convergence value (X ₂ ) must be estimated.

Here, the third coefficient of change W ₃ , the first coefficient of change W _1, and the first coefficient of change W ₂ have a correlation as shown in Equation 3 below.

In this case, k ₁ and k ₂ are correlation parameters previously stored in the parameter storage unit 140, which are parameters preset as measured values by a predetermined number of whole blood samples for which the concentration of hemoglobin in the blood can be known.

Therefore, each of the first absorbance estimating unit 142 and the second absorbance estimating unit 143 detects the correlation parameters k ₁ and k ₂ in the parameter storage unit 140 (S275), and is determined through <Equation 3>. The 1 coefficient of change W ₁ and the second coefficient of change W ₂ are estimated (S277).

Then, each of the first absorbance estimating unit 142 and the second absorbance estimating unit 143 inputs the estimated first coefficient of change W ₁ and the second coefficient of change W ₂ into <Equation 2> to converge the first absorbance. The value (X ₁ ) and the second absorbance convergence value (X ₂ ) are estimated (S279).

Then, the hemoglobin concentration in the blood of the whole blood may be calculated by the hemoglobin concentration calculation model 144 of the calculation unit 140 as shown in Equation 4 below.

Here, a and b are calibration coefficients depending on the measuring device/wavelength/cuvette optical path, etc., for example, a is a constant determining the discrimination power according to the hemoglobin concentration, and b is a correction constant.

Such a calibration coefficient may be initially calculated by measuring the absorbance of hemoglobin whose concentration is known, or may be performed at regular intervals when the blood hemoglobin measuring device 100 is installed or while the blood hemoglobin measuring device 100 is used.

In addition, the calibration coefficient is for correcting a slight difference in specifications according to a batch of the cuvette used in the blood hemoglobin measuring apparatus 100 of the present application. This difference in specifications may occur due to a difference in the optical path of the cuvette measurement area and a difference in the thickness of the plate forming the cuvette. For different specifications for each batch, the specifications for each batch can be input to the chip and used, and the calibration factor can be calculated from this. In addition, the calibration factor corrects the difference in measured values between cuvettes for the same hemoglobin concentration when a new batch of cuvettes is used in the blood hemoglobin measuring apparatus 100 of the present application.

In the above, the present invention has been described through embodiments with reference to the accompanying drawings, but the present invention is not limited thereto, and it should be interpreted to cover various modified examples that can be apparently derived from those skilled in the art. The claims are intended to cover these variations.

Claims (7)

A light irradiation unit that emits three different first wavelength incident light, second wavelength incident light, and third wavelength incident light;
A cuvette receiving portion configured to receive a cuvette for a whole blood sample;
A light detector configured to detect absorbance of incident light having a first wavelength to a third wavelength that has passed through the cuvette of the cuvette receiving portion;
A control unit controlling the light irradiation unit and the cuvette receiving unit to sequentially irradiate the sample of the cuvette with incident light having a first wavelength to a third wavelength, and controlling absorbance by the third wavelength incident light to be measured several times at predetermined time intervals;
The convergence value of the absorbance of the first wavelength to the third wavelength is estimated from the rate of change of the absorbance of the third wavelength measured several times, and the convergence values of the absorbance of the first wavelength to the third wavelength are estimated. A calculation unit that determines the concentration of hemoglobin in blood;
Blood hemoglobin concentration measuring device comprising a.
The method of claim 1, wherein the light irradiation unit
A first light source that outputs incident light with a first wavelength in the range of 400 to 420 nm, a second light source that outputs incident light with a second wavelength in the range of 800 to 830 nm, and a third light source that outputs incident light with a third wavelength in the range of 520 to 550 nm. 3 including a light source,
A device for measuring hemoglobin concentration in blood in which the first to third light sources are sequentially arranged.
The method of claim 2, wherein the control unit
A blood hemoglobin concentration measuring apparatus for controlling the light detection unit to obtain a plurality of third absorbance measurements by repeatedly driving a third light source within a predetermined time at a predetermined time interval.
The method of claim 3, wherein the control unit
A blood hemoglobin concentration measuring device for stopping driving of the third light source according to whether or not the decrease value of the third absorbance measurement value becomes equal to or less than a predetermined threshold.
The method of claim 4, wherein the calculation unit
A third absorbance estimating unit for estimating a third absorbance convergence value according to a third absorbance change rate estimated from the plurality of third absorbance measurements, and estimating a third absorbance change rate coefficient from the third absorbance convergence value and the third absorbance measurement value;
A parameter storage unit for storing a first correlation parameter between the first absorbance change coefficient and the third absorbance change coefficient, and a second correlation parameter between the second absorbance change coefficient and the third absorbance change coefficient;
The first correlation parameter detected in the parameter storage unit is multiplied by the third absorbance change factor to estimate the first absorbance change factor, and the estimated first absorbance change factor is multiplied by the first absorbance measurement value to calculate a first absorbance convergence value. 1 absorbance estimation unit;
The second correlation parameter detected in the parameter storage unit is multiplied by the third absorbance change factor to estimate the second absorbance change rate coefficient, and the estimated second absorbance change rate coefficient is multiplied by the second absorbance measurement value to calculate a second absorbance convergence value. 2 absorbance estimation unit;
A hemoglobin concentration calculation model for calculating a blood hemoglobin concentration of whole blood from the estimated first absorbance convergence value, the second absorbance convergence value, and the third absorbance convergence values;
Blood hemoglobin concentration measuring device comprising a.
The method of claim 1, wherein the light detection unit
A blood hemoglobin concentration measuring device that is attached to the bottom of the whole blood sample in the cuvette holder and moved together with the cuvette holder.
The method of claim 3, wherein the three light sources
A device for measuring hemoglobin concentration in blood that is sequentially disposed on one side of the housing and is moved from a fixed cuvette holder to a whole blood sample position.

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