JPH07113604B2 - Hemoglobin concentration measuring device - Google Patents

Description

DETAILED DESCRIPTION OF THE INVENTION [Industrial application] The present invention utilizes the absorption characteristics of hemoglobin in blood,
The present invention relates to a hemoglobin concentration measuring device that measures hemoglobin concentration in blood.

[Prior Art] Conventionally, hemoglobin concentration is measured by physically or chemically hemolyzing the collected blood, placing it in a cuvette, irradiating it with light of a specific wavelength, measuring the transmitted light, and measuring Hemoglobin concentration is calculated using Beer's law.

[Problems to be Solved by the Invention] However, the above method has a problem that continuous measurement is difficult because it is necessary to hemolyze the blood to be measured.

[Means for Solving Problems] An object of the present invention is to eliminate the need for hemolyzing blood to be measured,
Another object of the present invention is to provide a hemoglobin concentration measuring device capable of continuous measurement.

What achieves the above-mentioned object is a first light irradiating means for irradiating blood with a light having a wavelength whose absorption coefficient does not substantially change due to the oxygen saturation of hemoglobin in the blood, and a light having the same wavelength as the light into the blood. The second light irradiating means for irradiating is provided so that the distance from the first light irradiating means and the distance from the second light irradiating means are different from each other, and the first light irradiating means and the second light irradiating means are provided. Detecting means for detecting the intensity of light reflected from the blood by the light irradiating means into the blood;
First reflected light intensity signal based on the reflected light intensity of the light emitted by the light emitting means detected by the detecting means, and the light emitted by the second light emitting means detected by the detecting means. A correction coefficient calculating means for calculating a correction coefficient by using at least one of the second reflected light intensity signals based on the reflected light intensity, and a correction coefficient output from the correction coefficient calculating means are used by the detecting means. The first reflected light intensity signal based on the reflected light intensity of the light emitted by the first light emitting means that is continuously detected and the second light emitting means that is continuously detected by the detecting means. Corrected reflected light intensity ratio calculating means for calculating the corrected reflected light intensity ratio from the second reflected light intensity signal based on the reflected light intensity of the reflected light, and the corrected reflected light intensity output from the corrected reflected light intensity ratio calculating means. With ratio It is a hemoglobin concentration measuring device having a hemoglobin concentration calculating means for calculating a hemoglobin concentration in the solution.

The present invention will be described with reference to the embodiment shown in FIG.

The absorption (reflection) characteristics of blood change depending on the absorption and scattering of dyes and particles in blood, and in particular, as shown in FIG. 7, the absorption coefficient largely changes depending on the binding state of hemoglobin with oxygen and the irradiation wavelength. Here, HbO ₂ is oxygenated hemoglobin, Hbr is reduced hemoglobin, and HbCO is carbon monoxide hemoglobin. As can be seen from this figure, near the wavelength of 800 nm, HbO ₂ and Hbr cross each other and have the same extinction coefficient. This wavelength is called an isosbestic point wavelength, which means that the absorption coefficient does not change depending on the hemoglobin oxygen saturation in blood.

FIG. 8 and FIG. 9 show the experimental results for sample blood collected from three different individuals with 800 nm light, and the relationship between hemoglobin concentration and reflected light intensity is plotted. FIG. 8 shows the results when the distance between the light reception and the light emission is 0.25 mm, and FIG. 9 shows the results when the distance between the light reception and the light emission is 0.50 mm.
It should be noted that the measurement of the reflected light intensities is a result obtained by previously calibrating the reflected light intensities with a white reflector to a predetermined value.

The reflected light intensity when the distance between the received light and the emitted light is 0.25 mm is I ₁ , and the reflected light intensity when it is 0.50 mm is I _2, and the ratio
The relationship between I ₁ / I ₂ and hemoglobin concentration is shown in FIG. From FIGS. 8 and 9, it can be seen that the reflected light intensities are considerably affected by individual differences in blood, but can be reduced by taking the ratio as shown in FIG. However, it is still strongly influenced by the difference in the scattering characteristics of blood. It was also found that I ₁ and I ₂ did not change in the same tendency due to the difference in hemoglobin concentration. I ₁
Since the signal resulting from the hemoglobin concentration can be obtained by using the ratio of I and I ₂ , the present invention is utilized to measure the hemoglobin concentration.

Therefore, the apparatus of the present invention is a measurement capable of measuring the hemoglobin concentration of blood without being affected by individual differences in blood.

The hemoglobin concentration measuring device of the present invention is provided with the light irradiation means 1
A detecting means 2 for detecting the intensity of light reflected from the blood by the light irradiating means 1, and a correcting means 3.
It is formed by a hemoglobin concentration calculating means 4 for calculating the hemoglobin concentration using the output from the correcting means 3 and a display 5 for displaying the output from the hemoglobin concentration calculating means 3.

The light irradiating means 1 has a first light irradiating means and a second light irradiating means for irradiating blood with a specific wavelength.

In the structure shown in FIG. 1, the first light irradiating means and the second light irradiating means emit a light of a specific wavelength, a first light emitting source, and a second light emission of a light of a specific wavelength. And a light irradiator that irradiates the blood with light from each light source.

More specifically, the light irradiating means 1 comprises a light emitting source and a light irradiating unit for irradiating light from the light emitting source into the blood. The light emitting source is composed of two light emitting diodes 12 and 13. Numeral 13 is for emitting light of about 800 nm (λ ₂ ), which causes the pulse generator 14 to generate pulses having a predetermined time interval and a predetermined time width which do not overlap in time, and the light emitting diodes 12, 13 through the drive circuit 15. Are configured to emit light alternately. Then, the light emitted from the light emitting diode 12 passes through the optical fiber 18a for light emission and the optical fiber 18a.
The light is irradiated into the blood from the light irradiation unit 20 formed by the end surface of the. By doing so, the device can be downsized.

Further, the light emitted from the light emitting diode 13 passes through the optical fiber 18b for light emission and is irradiated into the blood by the light irradiation section 19 formed by the end face of the optical fiber 18b.

The light source is not limited to that shown in FIG. 1, but includes a common light-emitting source that emits light of a specific wavelength and two light-irradiating sections that irradiate light from this light-emitting source into blood from different positions. You may comprise.

The detection means 2 is for detecting the reflected light intensity from the blood of the light emitted from the light irradiation means 1. In the structure shown in FIG. 1, the light detecting section 21 of the detecting means 1 is formed by the end face of the optical fiber 18c for receiving light, and the distance from the light irradiating section 19 and the distance from the light irradiating section 20 are the same. It is provided differently.

FIG. 2 shows an end view of a specific example of the sensor probe 50 having the light irradiation units 19 and 20 of the light irradiation unit and the light detection unit 21 of the light detection unit.

Between the center of the light emitting part 20 formed by the end face of the light emitting optical fiber in which two light emitting optical fibers and one light receiving optical fiber are linearly arranged and the light detecting part 21 formed by the end face of the light receiving fiber. Is 0.25 mm, the distance between the centers of the light emitting portion 19 formed by the end face of the optical fiber for light emission and the light detecting portion 21 formed by the end face of the light receiving fiber is 0.50 mm, and between them They are provided at different distances and are fixed with an epoxy resin adhesive 52. As an optical fiber, multi-component glass,
A core diameter of 200 μm was used. The peripheral portion of the end surface of the sensor probe 50 is polished to have a smooth surface so as not to impair the light transmittance and to prevent thrombus. In the sensor probe described above, the number of the photodetection section 21 is one in order to make the sensor probe smaller, but the number is not limited to this, and the photodetection section may be composed of a plurality of pieces.

Then, FIG. 3 shows a state in which the sensor probe 50 is attached to a connector 56 which can be attached to an extracorporeal circulation circuit (not shown) such as an artificial heart-lung machine. Connector 56
Has an attachment port 58 for the sensor probe 50 protruding outward in the middle of its axial direction. The end surface of the sensor probe 50 is such that the inner wall surface of the connector 56 and the end surface of the sensor probe 50 are substantially flush when attached to the connector 56 so as not to disturb the blood flow flowing in the connector 56. It is processed.

The detection means 2 has a photodiode 16 and a detection amplifier 23 that receive the light detected by the light detection unit 21 and transmitted through the light receiving optical fiber 18c.
16 generates a current according to the intensity of the optical signal, and the detection amplifier 23
Is converted into a voltage signal. Further, the detection means 2 has a signal separation circuit for separating the voltage signal of the detection amplifier 23 into a signal corresponding to the light emission wavelengths of the light emitting diodes 12 and 13, and the signal separation circuit includes an analog switch 24 and a capacitor. 25, 26 and buffer amplifiers 28, 29.

The analog switch 24 has three switches, SW ₁ and SW ₂ , and each switch is "O" by a signal from the pulse generator 14.
N "OFF" For example, when the light emitting diode 12 emits light, the signal from the pulse generator 14 is applied to the analog switch 24, only SW ₁ is in the "ON" state, and the voltage signal of the detection amplifier 23 is the capacitor. Applied to capacitor 25 to generate an average signal voltage across capacitor 25.
The reflected light intensity of the wavelength λ ₁ received by the photodiode 16 via the photodetector 21 is reflected by the light emitted by the light irradiation unit 20 and reflected in the blood. This average signal voltage is continuously output through the buffer amplifier 28 and becomes the reflected light intensity signal I ₁ . Similarly, the same operation is performed by the combination of the light emitting diode 13, the SW _{2 of the} analog switch 24, the capacitor 26, and the buffer amplifier 29, and the reflected light intensity signal I ₂ of the wavelength λ ₁ of the light emitting diode 13 is output.

Further, the detection means 2 has a processing means of the signals of the reflected light intensity signals I ₁ and I ₂ output from the signal separation circuit, and the signal processing means digitally processes the reflected light intensity signals I ₁ and I ₂ . An analog-digital converter 31 for converting into a signal and a digitized reflected light intensity signal output from the analog-digital converter 31 a predetermined number of times (n times) or within a predetermined time
It has an average value calculator 32 that stores I ₁ and I ₂ and calculates an average value.

The correction means 3 has a correction coefficient calculation unit 40 and a corrected reflected light intensity ratio calculation unit 44. Correction coefficient calculator 40
Is the first reflected light intensity signal I ₁ and the second reflected light intensity signal I ₂
Using a measured reflected light intensity ratio calculation function 60 to calculate one reflected light intensity ratio (I ₁ / I ₂ ) using, the blood of the same animal species as the blood to be measured, and hemoglobin concentration is known, The reflected light intensity ratio and hemoglobin calculated from the data of the reflected light intensity ratio calculated from two reflected light intensity signals detected by irradiating light from two locations at different distances from the detection means (light receiving means) and hemoglobin concentration Correlation function h with concentration
(Rs) or its inverse function g (Hb) storage function, the hemoglobin concentration measurement value input unit 62, and the correlation function or its inverse function from the hemoglobin concentration measurement value of the blood to be measured input from the reflected light intensity ratio [ and I ₁ / I _2] calculated reflected light intensity ratio calculation function 65 for calculating the s, the more correction factors measured reflected light intensity ratio (I ₁ / I ₂₎ and the calculated reflected light intensity ratio [I ₁ / I _2] s And a correction coefficient calculation function 66 for calculating. Specifically, as shown in FIG. 3, the correction coefficient calculation unit 40 outputs one digitized reflected light intensity signal I ₁ , I ₂ output from the average value calculation unit 32.
And a calculation unit 60 for calculating the reflected light intensity ratio (I ₁ / I ₂ ) (in other words, a measured reflected light intensity ratio calculation function), and a measurement value input means 62 for sampling the measured blood and measuring the hemoglobin concentration thereof. Is a higher-order correlation curve (for example, a quadratic regression curve) calculated from the data of I ₁ / I ₂ and hemoglobin concentration Hb obtained from several kinds of blood of the measurement target animal species that have been measured in advance. Standard correlation function h (Rs) h (Rs) = b ₂ · Rs ² + b ₁ · Rs + b ₀ For example, h (Rs) = − 4.55 · Rs ² + 37.8 · Rs + −4.91 [where Rs = I ₁ / I ₂ , below, h (Rs) is called the Hb calibration curve] is the inverse function g (Hb) of the Hb calibration curve. The storage unit 64 and the reflected light intensity ratio [I ₁ / I ₂ ] s calculation unit 65 corresponding to the hemoglobin concentration input from the measured value input means from the inverse function g (Hb), in other words, the correlation function or Using the inverse function, the calculated reflected light intensity ratio calculation function for calculating the reflected light intensity ratio for the hemoglobin concentration value of the input blood to be measured, and [I ₁ / I ₂ ] s output from this calculation unit Is output from the calculation unit 60 (I ₁ / I ₂ )
More preferably, it comprises a calculation unit 66 for calculating the correction coefficient [I ₁ / I ₂ ] s / (I ₁ / I ₂ ) (= A).

The correction coefficient A output from the correction coefficient calculation unit 40 is the corrected reflection light intensity ratio together with the digitized reflection light intensity signals [I ₁ ] and [I ₂ ] continuously output from the average value calculation unit 32. It is input to the calculation unit 44. Then, the calculation unit 44 calculates the corrected reflected light intensity ratio Rs, Rs = A × [I ₁ ] / [I ₂ ] from the above signals.

That is, in the correction means 3, the ratio of the (reflected light intensity ratio calculated from the reference correlation function) and the (measured reflected light intensity ratio) for a known hemoglobin concentration. This is a correction means for obtaining the value of ## EQU1 ## and multiplying the value of this ratio as a correction coefficient by the reflected light intensity ratio which is successively measured thereafter, so-called span calibration is performed with a known hemoglobin concentration. The reason why a suitable corrected reflected light intensity ratio can be obtained by using I ₂ which is the reflected light intensity signal of the same wavelength together with I ₁ is not clear, but in consideration, I ₂ is a wavelength of 800 nm. Since this is a reflected light intensity signal of light and does not depend on the oxygen saturation, a constant value is basically detected. However, in a situation in which the hemoglobin concentration measuring apparatus according to the present invention is used, for example, in heart surgery, blood transfusion for supplementing bleeding during surgery, and infusion administration for fluid replacement are performed. As a result, the hemoglobin concentration changes. Also, if I ₁ changes due to some factor (eg, rapid partial change in blood flow, temporary defect of light receiving element, temporary decrease of supply voltage or current to decrease emission), it does not result from hemoglobin concentration. , I ₂ which is the reflected light intensity signal of the same wavelength light is also likely to change for the same reason. It is expected that such a change can be dealt with by using I ₂ for the calculation of the corrected reflected light intensity ratio.

Then, the hemoglobin concentration calculating means 4 calculates a higher-order correlation curve (I) from the data of I ₁ / I ₂ and hemoglobin concentration Hb obtained from several kinds of blood of the animal species of the measurement object which has been measured in advance. For example, a standard correlation function h (Rs), which is a quadratic regression curve, h (Rs) = b ₂ · Rs ² + b ₁ · Rs + b ₀ h (Rs) = − 4.55 · Rs ² + 37.8 · Rs + −4.91 [however, , Rs = I ₁ / I ₂ , hereinafter, h (Rs) is referred to as the Hb calibration curve.] Is stored, and the corrected reflected light intensity ratio Rs output from the calculation unit 44 Using the Hb calibration curve,
Calculate the hemoglobin concentration.

The signal output from the hemoglobin concentration calculation means 4 is displayed on the display 35. As the display device 35, a known device such as a cathode ray tube, a printer, a liquid crystal display device or a recorder may be used as long as it can notify the measured value to the outside.

Next, a hemoglobin concentration measuring method using the hemoglobin concentration device of the present invention will be described with reference to a flowchart shown in FIG.

(Example) In the example shown in FIG. 5, as step S1, the connector having the shape shown in FIG. 3 to which the sensor probe shown in FIG. 2 is attached is attached to the blood circuit.

In step S2, about 800 from the light irradiation section 19, 20 formed by the end surface of the optical fiber of the light irradiation means shown in FIG.
Light of nm (λ ₂ ) is sequentially irradiated into the blood, and the detection means 2 detects the reflected light intensity n times from the blood of each light emitted from the light irradiation means 1.

In step S3, the average value of the reflected light intensities detected n times is calculated, and the digitalized reflected light intensity signals I ₁ and I ₂ are output.

In step S4, it is determined whether to correct the hemoglobin concentration. If yes, step 5a and step 5b
Go to 1. In step 5a, the reflected light intensity ratio (I ₁ / I ₂ ) is calculated from the one (first output) digitized reflected light intensity signal I ₁ , I ₂ output in step 3.

In step 5b1, the measurement blood is sampled and the hemoglobin concentration thereof is measured.

As step 5b2, previously measured and calculated, from the data of I ₁ / I ₂ and hemoglobin concentration Hb obtained from several kinds of blood of the measurement target animal species stored, the calculated higher-order correlation curve ( For example, a standard correlation function h (Rs), which is a quadratic regression curve, h (Rs) = b ₂ · Rs ² + b ₁ · Rs + b ₀ h (Rs) = − 4.55 · Rs ² + 37.8 · Rs + −4.91 [however, , Rs = I ₁ / I ₂ , hereinafter h (Rs) is referred to as Hb calibration curve] is the inverse function g (Hb) of the Hb calibration curve The reflected light intensity ratio [I ₁ / I ₂ ] s corresponding to the hemoglobin concentration thus measured is calculated.

As step 6, output by step 5a (I ₁ / I
₂ ) and [I ₁ / I ₂ ] _S output by step 5b2,
A correction coefficient [I ₁ / I ₂ ] s / (I ₁ / I ₂ ) (= A), which is the ratio of the two, is calculated.

In step 7, it is determined whether to use the correction coefficient A calculated in step 6.

If it is determined that the correction coefficient A is used, the process proceeds to step 8, and the corrected reflected light intensity ratio R is calculated by the digitized reflected light intensity signals [I ₁ ] [I ₂ ] continuously output from step S3. _S , R _S = A × [I ₁ ] / [I ₂ ] is calculated.

When the correction coefficient A calculated in step 6 is not used, the process proceeds to step 9, and the digitized reflected light intensity signal [I ₁ ] [I ₂ ] continuously output from step 3 is used.
With, the reflected light intensity ratio R, R = [I ₁ ] / [I ₂ ] is calculated.

As step S10, several kinds of animal species of the measurement object which are measured and calculated in advance from the corrected reflected light intensity ratio R _S output from step S8 or the reflected light intensity ratio R output from step S9 are stored. I ₁ / I ₂ obtained from blood
And the hemoglobin concentration Hb, the reference correlation function h is a higher-order correlation curve (for example, a quadratic regression curve) calculated from the data.
(Rs), h (Rs) = b 2 · Rs 2 + b 1 · Rs + b 0 h (Rs) = - 4.55 · Rs 2 +37.8 · Rs + -4.91 [ _{where, Rs = I 1 / I 2} , less, h (Rs) is referred to as an Hb calibration curve] The hemoglobin concentration is calculated using the Hb calibration curve.

In step S11, the hemoglobin concentration output in step S10 is displayed.

In step S12, it is determined whether the measurement is to be ended. If not, the process returns to step S2 to repeat the measurement.

The hemoglobin concentration obtained by this example and the OSM2 hemoximeter used as a control (manufactured by Radiometer)
FIG. 6 shows the relationship with the hemoglobin concentration measured in.
From these results, the value (x) of hemoglobin concentration obtained by the method of the present invention was compared with the value (y) of hemoglobin concentration by the OSM2 hemoximeter, and the correlation coefficient was 1 (y =
It was confirmed that the measurement was extremely close to x) and the error (SD) was sufficiently small to enable accurate measurement.

[Effects of the Invention] The hemoglobin measuring apparatus of the present invention has a first light irradiating means for irradiating blood with a wavelength of which the absorption coefficient does not substantially change due to the oxygen saturation of hemoglobin in blood, and the same wavelength of the light. Second light irradiating means for irradiating blood into the blood and the first
Of the light radiated into the blood by the first light irradiating means and the second light irradiating means, the distance from the light irradiating means is different from the distance from the second light irradiating means. Detecting means for detecting the intensity of the reflected light from the blood; a first reflected light intensity signal based on the intensity of the reflected light detected by the detecting means of the light emitted by the first light emitting means; Correction coefficient calculating means for calculating a correction coefficient using at least one of a second reflected light intensity signal based on the reflected light intensity detected by the detecting means of the light emitted by the light emitting means, and the correction coefficient A first reflected light intensity signal based on the reflected light intensity of the light emitted by the first light emitting means that is continuously detected by the detecting means using the correction coefficient output from the calculating means, and the detecting means. Continuously detected by And a corrected reflected light intensity ratio calculating means for calculating a corrected reflected light intensity ratio from a second reflected light intensity signal based on the reflected light intensity of the light emitted by the second light emitting means, and the corrected reflected light intensity ratio. Since it has a hemoglobin concentration calculation means for calculating the hemoglobin concentration in blood using the corrected reflected light intensity ratio output from the calculation means, it is not necessary to hemolyze the blood to be measured, and the hemoglobin concentration can be continuously measured. It can be measured accurately and easily.

[Brief description of drawings]

FIG. 1 is a block diagram of an embodiment of a hemoglobin concentration measuring device of the present invention, FIG. 2 is an end view showing an example of a sensor probe used in the hemoglobin concentration measuring device of the present invention, and FIG. 2 is a cross-sectional view of the connector to which the sensor probe shown in FIG. 2 is attached, FIG. 4 is a block diagram showing a specific example of the correction coefficient calculation unit in the block diagram of FIG. 1, and FIG. 5 is an embodiment of the present invention. FIG. 6 is a flowchart showing a hemoglobin concentration measuring method by the hemoglobin concentration measuring device of FIG. 6, FIG. Fig. 7 is a diagram showing the relationship with Fig. 7, Fig. 7 is a diagram showing the absorption characteristics of blood, and Figs. 8 and 9 show that light with a wavelength of about 800 nm was irradiated at different distances. Shows by plotting the relationship between reflected light intensity and hemoglobin concentration, Fig. 10, I ₁ the reflected light intensity when the interval of the light receiving and emission of 0.25 mm, 0.50 mm
The reflected light intensity and I ₂ in the case of a diagram showing the relationship between their ratio I ₁ / I ₂ and hemoglobin concentration. 1 ... Light irradiating means, 2 ... detecting means, 3 ... correcting means, 4 ... hemoglobin concentration calculating means, 5 ... display, 12,13 ... light emitting diode, 14 ... pulse generator, 15 ... … Drive circuit, 18a, 18b, 18c …… Optical fiber 19,20 …… Light irradiator, 21 …… Photodetector, 16 …… Photodiode, 23 …… Detecting amplifier 24 …… Analog switch, 28,29 …… Buffer amplifier, 42 …… Correction coefficient calculator, 44 …… Corrected reflected light intensity ratio calculator, 50 …… Sensor probe, 56 …… Connector 58 …… Port

Claims (10)

[Claims] 1. A first light irradiating means for irradiating blood with light having a wavelength whose absorption coefficient does not substantially change due to the oxygen saturation of hemoglobin in the blood, and a first light irradiating means for irradiating blood with light of the same wavelength as the light. The second light irradiation means is provided so that the distance from the first light irradiation means is different from the distance from the second light irradiation means, and the first light irradiation means and the second light irradiation are provided. Detecting means for detecting a reflected light intensity of the light radiated into the blood by the means, and a first means based on the reflected light intensity of the light radiated by the first light radiating means detected by the detecting means. Of the reflected light intensity signal and the second reflected light intensity signal based on the reflected light intensity of the light emitted by the second light emitting means detected by the detecting means, the correction coefficient is calculated. Correction coefficient calculating means for Using the correction coefficient output from the arithmetic unit,
A first reflected light intensity signal based on the reflected light intensity of the light emitted by the first light irradiation unit that is continuously detected by the detection unit, and a second light irradiation that is continuously detected by the detection unit. A corrected reflected light intensity ratio calculation means for calculating a corrected reflected light intensity ratio from a second reflected light intensity signal based on the reflected light intensity of the light emitted by the means, and the corrected reflected light intensity ratio calculation means outputs the corrected reflected light intensity ratio calculation means. A hemoglobin concentration measuring device, comprising: a hemoglobin concentration calculating means for calculating the hemoglobin concentration in blood using the corrected reflected light intensity ratio. 2. The hemoglobin concentration measuring device according to claim 1, wherein the light irradiating means comprises a light emitting source and a light irradiating unit for irradiating blood from the light emitting source into the blood. 3. The first light irradiating means and the second light irradiating means irradiate a common light emitting source that emits light of the specific wavelength and light from the light emitting source into blood from different positions. To do 2
Claim 1 which consists of two light irradiation parts.
Item 2. A hemoglobin concentration measuring device according to item. 4. The detecting means is one detecting means for detecting respective reflected light intensities of the light emitted from the blood by the first light emitting means and the second light emitting means. The hemoglobin concentration measuring device according to any one of claims 1 to 3, which comprises: 5. The detecting means comprises a plurality of detecting means for detecting the intensity of reflected light from the blood, which is the light irradiated into the blood by the first light irradiating means and the second light irradiating means. The hemoglobin concentration measuring device according to any one of claims 1 to 4, which is a thing. 6. The hemoglobin concentration measurement according to any one of claims 2 to 5, wherein the light irradiating section is constituted by an end face of an optical fiber for transmitting light from a light emitting source. apparatus. 7. The detecting means includes a photodetector, a light transmitting section for transmitting light to the photodetector, and a photodetecting section, wherein the photodetecting section is an optical fiber forming the light transmitting section. The hemoglobin concentration measuring device according to any one of claims 1 to 6, which is constituted by an end face. 8. The hemoglobin concentration measuring apparatus according to claim 1, wherein the wavelength is about 800 nm. 9. The actually measured reflection for calculating one reflected light intensity ratio (I ₁ / I ₂ ) by the correction coefficient calculation means using the first reflected light intensity signal and the second reflected light intensity signal. Light intensity ratio calculation function and two reflected light intensities detected by irradiating blood of the same animal species as the blood to be measured and having a known hemoglobin concentration with light of the above wavelength from two different distances from the detection means. The correlation function h (Rs) between the reflected light intensity ratio calculated from the signal and the hemoglobin concentration calculated from the data of the hemoglobin concentration and the inverse function g (H
b) memory function, hemoglobin concentration measured value input section,
From the hemoglobin concentration measurement value of the blood to be measured input with the correlation function or its inverse function, the reflected light intensity ratio [I ₁ / I
₂ ] s, a calculated reflected light intensity ratio calculation function, and a correction coefficient calculation that calculates a correction coefficient from the measured reflected light intensity ratio (I ₁ / I ₂ ) and the calculated reflected light intensity ratio [I ₁ / I ₂ ] s The hemoglobin concentration measuring device according to any one of claims 1 to 8, which has a function. 10. The hemoglobin concentration calculating means calculates the hemoglobin concentration in blood by using the stored correlation function or its inverse function and the corrected reflected light intensity ratio output from the corrected reflected light intensity ratio calculating means. The correlation function or the inverse function thereof is obtained by irradiating blood of the same animal species as the blood to be measured and having a known hemoglobin concentration with light of the wavelength from two different distances from the detection means. It is a correlation function h (Rs) or its inverse function g (Hb) between the reflected light intensity ratio calculated from the two reflected light intensity signals detected and the data of the reflected light intensity ratio and hemoglobin concentration. The hemoglobin concentration measuring device according to any one of claims 1 to 9.