JPS6037896B2 - jaundice meter - Google Patents

Description

DETAILED DESCRIPTION OF THE INVENTION The present invention relates primarily to a yellow value meter for measuring bilirubin in newborn blood.

After birth, a newborn's environment changes significantly from inside the mother's body to outside the mother's body, but oxygen, which is essential for growth, is transferred from gas exchange within the mother's body via the placenta to its own lungs after birth. Oxygen can be taken directly from the air.

As a result, outside the mother's body, the amount of hemoglobin, a substance that carries oxygen inside the mother's body, which was required in large quantities within the mother's body, is not needed as much as when inside the mother's body.

Hemoglobin that is no longer needed is broken down and eventually excreted from the body as bilirubin, but in newborns, this amount of bilirubin increases, so bilirubin accumulates in subcutaneous fat, causing a symptom called neonatal yellowing. When the amount of bilirubin exceeds a certain limit, it not only accumulates in subcutaneous fat but also partially deposits in brain cells, resulting in a condition called keranpox.

If the patient develops yellow keratosis, he or she may die or have residual effects such as cerebral palsy, so such situations must be avoided.

Therefore, during the neonatal period, it is necessary to constantly measure the bilirubin concentration in the blood and take appropriate measures. Generally, to measure bilirubin, the simple colorimetric method according to the present invention is used because it is easy to handle, the measurement time is short, and the amount of blood collected is small.

A simple colorimetric method shows that bilirubin has a yellow color and 45
It particularly absorbs light with a wavelength around 5.5 yen (specific absorption wavelength light), and taking advantage of the fact that the yellow hue differs depending on the degree of bilirupine contained in serum, 45 yen is added to serum.
The amount of bilirubin can be determined by shining light around 5 mm and measuring the amount of transmitted light.

However, in general, serum contains hemoglobin, which is a blood pigment, in addition to bilirubin, so if you try to measure the bilirubin concentration by irradiating the serum with light with a specific wavelength of 455 m, it is difficult to measure the bilirubin concentration even if the hemoglobin in the serum is There is some absorption, which causes a measurement error.

It is therefore necessary to correct for the influence of hemoglobin.

Correcting this effect of hemoglobin is generally called dish correction.

To explain this using the characteristic diagram in Figure 1, in the diagram, 1 indicates the measurement curve of the sample serum, 0' indicates the measurement curve of only the pirirubin concentration, and m indicates the measurement curve of only hemoglobin concentration.
As you can see from the diagram, the wavelength of hemoglobin is 45 and 575.
The absorbance in the glue is approximately equal.

On the other hand, there is a direct proportional relationship between bilirubin concentration and absorbance at a wavelength of 455, and the absorbance of bilirupin at a wavelength of 575 is considered to be almost zero compared to the absorbance at a wavelength of 455. By determining the absorbance at 455 points and subtracting the absorbance at 575 points from this, it is possible to measure the correct concentration of pirirupine corrected for the plate.

Expressing the above using a formula, in Figure 1, 455
The measured value of absorbance OD455 at mr is OD455
=KHb455・Hb10Kb455・B.・．． ．．・．． [
1'Also, the absorbance at 575 in serum OD575
The measured value is ・OD575=KHb575・Hb×Kb5
75・B...■ However, in the above formulas [1} and '2), the absorption coefficient of hemoglobin in the mountains of KHb455:455, the absorption coefficient of hemoglobin in the Buddha of KH455:455, and the absorption coefficient of hemoglobin in the mountains of KHb575:575. Absorption coefficient of hemoglobin at # of Kb455:455, absorption coefficient of bilirubin at # of Kb575:575,
．． Hb: Hemoglobin concentration B: Bilirubin concentration Therefore, from the above formula [1] (2), the bilirubin concentration is K
'3 as b ni 0, B=K; principle (〇D455-Confession man X.

D575)...In this), each absorption coefficient becomes a constant value depending on the wavelength distribution situation, etc. (3' formula is B=K[OD455-
k・OD575]・. ．．・．． ．． '4}.

However, K: Far and Weak 5K: Instrument Refinement Next, a conventional example of a yellow direct meter using the above-mentioned bilirubin concentration measurement principle will be explained with reference to the efficiency diagram in Figure 2 and the light receiving measurement circuit diagram in Figure 3. .

First, the light from the light source A is made into an intermittent light by a chopper B to eliminate the influence of drift in the intensifier after receiving the light, and then passes through the adiabatic correction filter C and the condensing lens D, and is switched manually. The sample serum collected in the hematocrit Z tube F passes through an interference filter E with a 455-meter filter. This transmitted light passes through a slit G for preventing the influence of scattered light and is received by a light receiving element such as a photocell, and after being amplified by a light receiving measurement circuit 1, it is sent to an indicator J.
It is now instructed to do so. ZNext, to explain how to operate the yellow value meter, first, zero correction of the light receiving measurement circuit 1 is performed.
This is to ensure that the indication of the indicator J becomes the same value 2 when switching between the enemy Ea and the 575 Buddha Eb. That is, this is to eliminate the influence on the final indicator J due to differences in the transmission amount of the interference filter E and the spectral characteristics of the light receiving element.

So, specifically,
21-{1) Set the calibration circuit K to a non-operating state.
1-■ Pour distilled water into the hematocrit tube F.

1-(3-Switch the interference filter E to 455 skin Buddha Ea.

1-{4- Adjust the zero adjustment regulator L and turn on the indicator 3.
Let J's instruction be zero.

1 Switch the kick interference filter E to 575m〃Eb1
-(6) Set the indication of indicator J to zero using balance adjuster M. At this time, interference filter E and switch N and 3 are linked, and balance adjustment is performed only when interference filter E is switched to 575mrb. The device M and constant circuit 0 are now operational.

1-{7} Switch the interference filter E to 455 mm Ea again.

This completes the zero correction before measurement.

, Next, calibrate the indicator J to the standard value using the standard solution or an optical aperture equivalent to the standard solution.

That is, 2-{1} A bilirubin standard solution is put into the hematocrit tube F.

2" 21 Adjust the indicated value of the indicator J to the indicated concentration value of the bilirubin solution using the standard regulator P. 2"3' Switch the 1,100 filters E of 575.

With the above steps, the measurement preparations are completed and the measurement begins. 3-2' A calibration circuit K sets the indication of the indicator J to zero.

The 3-3l interference filter E is switched to 455 kite-1 Ea, and the indication from the indicator J at that time is displayed as the bilirubin value.

In FIG. 3, Q is an amplifier, R is a detection circuit, S is an integration circuit, T is a logarithmic amplifier, U is a DC amplifier, and V is an arithmetic circuit.

As explained above, the operation of the conventional jaundice meter is very complicated, and there is a possibility that the measured value may be wrong due to manipulation during operation, and a considerable heat source is required for the measurement operation.

Further, there were other drawbacks, such as complicated operations and the need for manual switching of the interference filter E, which took a long time to perform measurements.

The present invention seeks to eliminate the drawbacks of the above-mentioned subsidiary examples,
It is an object of the present invention to provide a yellow value meter equipped with light having a specific absorption wavelength of bilirubin and a wavelength for correcting absorption of hemoglobin (hemolysis correction) in the light of the wavelength.

The present invention will be described in detail with reference to illustrated embodiments. FIG. 4 is a system diagram of a Kizaru meter used in the present invention. The light is then condensed by a condenser lens 4.

The steps up to this point are the same as the conventional example, but in the present invention, in order to zero-correct the device, there is provided a data storage body 5 containing distilled water, a standard calibrator, and a sample for measurement, and a filter element 6a.
, 6b, and the filter housing 6 having filter housings 6a and 6b are moved in synchronization. That is, when the document storage body 5 is located at the position of distilled water,
Similarly, when the data storage body 5 is located at the position of the standard calibration body and the sample, respectively, the filter elements 6a and 6b are automatically switched on the optical path at least once each in synchronization with the data storage body 5. ing.

Further, the filter storage body 6 includes filter elements 6a and 6b.
A synchronous signal generating element 8 is provided for generating a signal synchronized with the synchronous signal.

The wavelength light that has passed through the filter elements 6a and 6b alternately passes through the materials in the material storage unit 5, becomes an optical signal, is converted into an electrical signal by a photoelectric conversion element 10 such as a photocell in the light receiving measurement device 9, and then is amplified. Perform intermediate processing and give an instruction using the indicator 11.

An embodiment of the synchronization mechanism for the above-mentioned document storage body 5 and filter storage body 6 will be described with reference to FIGS. 5, 6, 7, and 8. First, the embodiments shown in FIGS. 5 and 6 show a rotationally movable synchronous sliding mechanism, in which the material storage body 5 has a cylindrical hematocrit support surface 13 rotatably mounted in a fixed support body 12. Provided for. And the bearing cylinder 1
3 is formed with a groove 15 for inserting each of the hematocrit tubes 14 for distilled water, standard solution, and specimen, and the groove 15 is formed with a slit 16 that penetrates into the hematocrit support cylinder 13. has been done.

Also, through holes 17 are formed in the cylinder wall of the hematolite support cylinder 13 facing the slits 16 of the respective grooves 15, and through holes 18a, 18a are formed in the support body 12, facing the slits 16 of the grooves 15, respectively.
18b and the light is transmitted from the through hole 18a to the through hole 17.
, passes through the slit 16 and into the through hole 18b. A gear 19 is fixed to the lower end of the hematocrit bearing bridge 13, and this gear 19 rotates when it meshes with a sector gear 21 fixed to the rotating shaft of the motor 20 and having teeth in a range of about 120 degrees. It has become.

That is, the motor 20 rotates, and the sector gear 21 and gear 1
When the gears 9 are engaged, the gear 19 rotates about 120 degrees, and the hematocrit support cylinder 13 is sequentially rotated about 120 degrees so that the hematocrit tube 14 is located on the optical path.

In order to accurately stop the hematocrit tube 14 on the optical path at this time, a stop portion 24 is provided in which a spring 22 presses the sphere 23 against a groove formed in the hematocrit support tube 13 to stop it.

Although not shown, the gear 19 is equipped with a switch circuit for automatically stopping the motor 20 when the gear 19 rotates once, so that the motor 20 is stopped at a predetermined location after the measurement is completed.

When the switch circuit is released during measurement, the hematocrit bearing surface 13 intermittent rotates approximately 120 degrees each time the motor 20 rotates due to the action of the sector gear 21 and the gear 19. The hematocrit tubes are sequentially positioned on the optical path.

The filter storage body 6 has two filter elements 6a, 6b and synchronization holes 26a, 26b arranged in parallel on a square plate 25, and an arm 27 extending downward from the square plate 25 is supported by a shaft 28. , which is configured to swing from side to side with the shaft 28 as a fulcrum by means to be described later.

As a result, the filter elements 6a and 6b are alternately positioned on the optical path, but one filter element 6a is always positioned on the optical path due to the tensile force of the spring 29.

The three-way cam is fixed to the rotating shaft of the motor 20 like the sector gear 21, and the three-way cam has an oval-shaped part and a short-circular part.

The lower end of the arm 27 is connected to the cam 30 by the spring 29.
The arm 27 is in elastic contact with the sector gear 21 and the gear 19.
When the engagement with the cam 30 is completed, the cam 30 comes into contact with the short diameter portion of the cam 30. As a result, in FIG. 6, the square plate 25 rotates clockwise about the shaft 28, and the other filter element 6
b is positioned on the optical path.

When the cam 30 rotates another 1200 times, the arm 27 comes into contact with the elliptical diameter portion, and as a result, the rectangular plate 25 moves counterclockwise, and the filter element 6a is now positioned on the optical path.

In this way, the motor 20 rotates the hematocrit bearing cylinder 1 by the action of the sector gear 21 and the gear 19 in one rotation.
When 3 is rotated about 120 degrees) arm 27 and cam 3
0, due to the action of the spring 29, the filter elements 6a, 6
b alternately positioned on the optical path, and -times of measurement are completed in three rotations.

Note that the synchronization holes 26a and 26b are provided because the synchronization signal generation element 8 is constructed using a light emitting diode and a light receiving diode, but the synchronization signal generation element 8 may be formed using other known methods, such as It may be configured by a mechanical switch, a Hall element, or the like.

Next, the embodiments shown in FIGS. 7 and 8 show a linearly moving type synchronous cutting mechanism.

That is, the material storage body 5 includes a rectangular support box 31 and the box 31.
Each hematocrit tube 14 for distilled water, standard solution, and sample is arranged in series at a constant distance from the hematocrit support 32. ing.

Linear teeth 33 are provided on the lower surface of the support box 31 in the longitudinal direction, and the linear teeth 33 mesh with the sector gear 21 fixed to the rotating shaft of the motor 20.

On the other hand, the filter storage body 6 is configured to move in the vertical direction, and one filter element 6a is always positioned on the optical path due to the pressing force of the spring S.

Further, a cam 34 fixed to the rotating shaft of the motor 20 is connected to the bottom surface of the filter housing 6.
As a result, the filter housing 6 moves up against the pressing force of the spring S, and another filter element 6b is positioned on the optical path.

In the figures, the same reference numerals in the embodiments shown in FIGS. 6 and 7 indicate the same parts, and the movement relationship between the material storage body 5 and the filter storage body 6 is also the same as in the embodiments described above. is set to .

Further, the number of specimens to be stored is not limited to one, but may be multiple.

Next, the operation of the light receiving measurement device 9 will be explained.

The light receiving and measuring device 9 is roughly divided into the following types of operations.

■ When the hematocrit support cylinder 13 is in the position of distilled water, the light source lamp 1, lens 4, filter elements 6a, 6b
, including the spectral characteristics of the photoelectric conversion element 10, etc., to make the magnitude of the signal from the two wavelength lights (mountain 45, skin Buddha 575) the same.

In other words, zero correction is performed.

(2) When the hematocrit support cylinder 13 is in the position of the standard calibration body, adjust the indicated value of the indicator 11 to a value predetermined as the standard calibration body.

■ When the data storage body is in the position of a sample for leakage, the influence of hemoglobin is corrected (hemolysis correction) and the bilirubin value is displayed in a linear format.

Below, ① to ② will be explained in detail with reference to FIGS. 6 and 9. When the hematocrit tube containing distilled water is on the optical path due to the rotation of the hematocrit support cylinder 13 in the data storage body 5, the photoelectric conversion element 10 converts the measurement light (455 ㎇〃) and the hemolysis correction light (575 ㎇〃). The optical signal is converted into an electrical signal and amplified by an amplifier 35.

The switch circuit 36 operates in synchronization with the synchronization signal generating element 8. In the example of FIG. 9, the switch circuit 36 can compete with the measurement light (45), that is, when the measurement light is used, the signal from the amplifier 35 passes through the switch circuit 36 to the detector 3.
Leads to 7.

The signal detected by the wave detector 37 is integrated by an integrating circuit 38 and logarithmically amplified by a logarithmic amplifier 39 to become a bilirubin signal, which reaches the synchronous switch circuit 40.

Like the switch circuit 36, the synchronous switch circuit 40 operates in synchronization with the synchronous signal generating element 8.

That is, the bilirubin signal passes through the synchronous switch circuit 40, enters the hold circuit 41, and is stored. On the other hand, the signal of the hemolysis correction light (575 m peak) is amplified by the amplifier 35 and then transferred to the attenuator 45 and the detector 37 by the movement of the switch circuit 36.
, an integration circuit 38, a logarithmic amplifier 39, the hemolysis correction signal is switched by a synchronous switch circuit 40, and a differential amplifier 4
2 to one of the input terminals. The differential amplifier 42 is connected to an attenuator 45 via a switch circuit 43 and a hold circuit 44 so that the difference between the level of the bilirubin signal stored in the hold circuit 41 and the level of the hemolysis correction signal becomes zero.
control automatically.

That is, zero correction can be performed by controlling the attenuator 45 so that the difference in level between the bilirubin signal and the hemolysis correction signal becomes zero when the material storage body 5 is in the position of distilled water.

Here, the switch circuit 43 is connected to the hematocrit bearing cylinder 1.
3 is in the position of distilled water, and is closed when the data storage body 5 is a standard calibration body or a specimen to be measured.

Therefore, the control output of the differential amplifier 42 is the hold 0 circuit 4
4, it is held until the end of the measurement.

Note that a plate correction signal may be stored instead of the bilirubin signal.

The above operation is for distilled water, but in the case of a standard calibrator and a sample, the output of the logarithmic amplifier 39 is directly input to the amplifier 46.

That is, the output from the logarithmic amplifier 39 is OD455 and OD575 in synchronization with the synchronizing signal generating element 8, and is supplied to the next stage amplifier 46.

The synchronous switch circuit 47 and the constant circuit 48 together with the amplifier 46 form a feedback amplifier circuit, and the synchronous switch circuit 47 outputs 455 clock information and 575 desk information synchronized with the synchronous signal generating element 8. ing.

Here, in order to explain the action of the circuit, we replace K=Q・8・7, where: Q: Amplification factor of the differential amplifier 50 8: Amplification factor of the feedback amplifier circuit ↑: Indication sensitivity coefficient of the indicator 1 The above [4-formula B=K [〇D455-k, 〇D575] is B=Q・Ding [8・CD455-8・k. OD575] [Replaced with 51.

The constant circuit 48 operates so that the ratio of the amplification factors of the feedback amplifier circuit to the two inputs is k, for example, the amplification factor for OD455 is B, and the amplification factor for OD575 is 8.k. It is preset to do so.

In this case, the magnitude of the above two outputs output from the synchronous switch circuit 47 is 8・OD455 in the formula [5}.
and B.k.OD575.

That is, the synchronous switch circuit 47 operates in conjunction with the synchronous signal generating element 8 which operates in synchronization with the filter elements 6a and 6b of the filter housing 6 shown in FIG. The synchronous switch circuit 47 falls downward,
The amplification factor of the feedback amplifier circuit is set to B·k, and the output signal of the amplifier 46 is input to a hold circuit 49 and held therein. The signal held in the hold circuit 49 is 8
・k・OD575, which is input to one terminal of the difference amplifier 50. On the other hand, in the case of 455 m French, the synchronous switch circuit 47 falls upward, and the amplification factor of the feedback amplifier circuit is set to 3, and the output signal of the amplifier 46 is 8.OD4.
55 is input to the other terminal of the active amplifier 50.
The differential amplifier circuit 5 serves to subtract 3.k.OD575 stored in the hold circuit 49 and 8.k.OD455 directly input from the amplifier 46. In other words, the difference in input to the differential amplifier is P・OD45 in the formula '5) above.
5-B.k.OD575, and the output supplied to the indicator 11 is Q[8.OD455-B.k.00575], which is obtained by multiplying this by the amplification factor Q of the differential amplifier circuit 50.

The standard calibration circuit 51 is provided to manually adjust the indicated value to the numerical value (standard value) determined as the standard calibration body when the hematocrit support cylinder 13 is in the standard calibration body position. The standard calibration circuit 51 adjusts the output to the indicator 11 so that the indicator 11 indicates the standard value. That is, Q is adjusted so that Q.817=K. In this way, the indicator 1 will show the value adjusted so that Q・8・7=K in the formula '5), and in the end it will be adjusted to indicate the value B in the formula (4}. Become.

Through the above operations, when the hematocrit supporting lacquer tube 13 is at the sample position, the amplifier 46 and the synchronous switch circuit 4
7, constant circuit 48, hold circuit 49, differential amplifier 50
, the standard calibration circuit 51, etc., and the measured value of the specimen is indicated to the indicator 11 in a direct connection manner.

In addition, in the above explanation, k is added to OD575 for convenience, but it is only necessary that the amplification factor ratio of the feedback amplifier circuit is k, and it is sufficient to add k to OD575 or both OD575 and CD45. It is clear that the OD455 may be increased by 1/k, for example. In other words, (5-When formula is transformed, B=.

・7(k/k) [8・OD455-8・k・OD575
]=.

・↑・k [(B/k)・OD455-8・OD575]
Then? Since is the indicator sensitivity coefficient of the indicator 11, k may be included, and it is natural if we assume that ka·k=↑' and consider T' to be the new indicator sensitivity coefficient.

FIG. 10 shows another embodiment of the light receiving measuring device. The optical information converted into an electrical signal by the photoelectric conversion element 10 is amplified by an amplifier 52, and then sent to an attenuator 54 by a switch circuit 53.
There are two routes: one that goes through the attenuator 55 to the detector 56, and the other that goes through the attenuator 55 and reach the detector 56. For example, in the case of measurement light (455 peak), the signal that has passed through the switch circuit 53 and attenuator 54 is detected by a detector 56, converted into a DC signal by an integrating circuit 57, and logarithmically converted by a logarithmic amplifier 58.

The logarithmically converted French signal of 455, that is, the bilirubin signal, reaches a switch circuit 59, but the switch circuit 59 is closed only when the hematocrit tube containing distilled water in the hematocrit support tube 13 is on the optical path.

The bilirubin signal is passed from the switch circuit 59 to the ratio Z shark circuit 6 and then to the reference circuit 60', where it is compared with the reference voltage (constant voltage) of the quasi-voltage circuit 61, and the difference voltage is determined by the switch circuit 62. It enters the hold circuit 64.

The hold circuit 64 connects the bilirubin signal to the reference voltage Z circuit 6.
Attenuator 5 so that it has the same magnitude as the reference voltage of 1
4 and keep this state until the end of the measurement. Similarly, one signal of the 575, that is, the melt plate correction signal, passes through the switch circuit 53 and the attenuator 55, reaches the switch circuit 62, and enters the hold circuit 63 by the action of the switch circuit 62.

The hold circuit 63 controls the attenuator 55 so that the reference voltage of the reference voltage circuit 61 and the plate correction signal have the same magnitude as the field of the bilirubin signal, and continues to maintain this state until the end of the measurement.

This is how zero correction can be performed. When the hematocrit tube in the hematocrit support cylinder 13 is at the position of the standard calibration object or specimen, the output signal of the logarithmic amplifier 58 enters the amplifier 46. Constant circuit 48 and synchronous switch circuit 4
Reference numeral 7 and amplifier 46 form a feedback amplifier circuit, and operate to determine the amplification ratio k of the feedback amplifier circuit for two inputs in the same manner as in FIG. Here, the synchronous switch circuits 47 and 47' work in synchronization with the synchronous signal generating element 8.

That is, it operates in synchronization with one signal of 455 skin and 575.

For example, in the case of a French signal of 575, the amplifier 46 works together with the synchronous switch circuit 47 and the constant circuit 48 to
- Operates to determine k. On the other hand, when the signal is 455, the same amplifier 46 operates in conjunction with the synchronous switch circuit 47 and the constant circuit 48 to determine 8 of the '5-type. Since k' of the constant circuit 48 takes a fixed value, it can be set in advance.

In the case of a peak signal of 575, the output signal of the amplifier 46 is stored in the hold circuit 49 via the synchronous switch circuit 47'.

The synchronous switch circuit 47' is closed only when there is a 575 slope/mountain signal. On the other hand, the peak signal of 455 is directly connected from the amplifier 46 to one input terminal of the differential amplifier 50, and is subtracted by the signal of the hold circuit 49, that is, the 575 skin signal, and the function of the differential amplifier 50. The difference signal is displayed on the indicator 11 as a standard value or a measured value. The standard calibration circuit 51 forms a feedback circuit for the differential amplifier 50, and when the hematocrit bearing cylinder 13 is in the position of the standard calibration body, the displayed value of the indicated value 11 is manually adjusted to the standard value determined as the standard calibration body. It is designed to match.

The hold circuit in the two embodiments described above is composed of, for example, a high input impedance amplifier such as an FET input amplifier and a capacitor. is employed, but other known methods may be used instead.

By configuring the present invention as described above, there is no need for complicated operations prior to measurement as in the conventional example, so measurement does not require any skill, and measurement values can be easily, quickly, and accurately obtained. be able to.

[Brief explanation of the drawing]

Fig. 1 is a characteristic diagram showing the relationship between wavelength and absorbance in serum, Fig. 2 is a system diagram showing a conventional jaundice meter, Fig. 3 is a light receiving measurement circuit diagram of the same jaundice meter, and Fig. 4 is a system diagram of the yellow pox meter according to the present invention, FIG. 5 is a cross-sectional explanatory diagram of the synchronous switching mechanism in the same yellow pox meter, FIG. 6 is a perspective view, and FIG. 7 is an embodiment of the synchronous switching mechanism. FIG. 8 is a perspective view, FIG. 9 is a circuit diagram of the light receiving measurement device of the jaundice meter according to the present invention, and FIG.
The figure is a circuit diagram showing another embodiment of the same light receiving measuring device. 1...Light source, 2...Chopper, 3...Insulation correction filter, 4...Condensing lens, 5...Data storage, 6...Filter storage Body, 6a, 6b・
... Filter element, 8 ... Synchronization signal generating element, 9 ... Light receiving measurement device, 10 ...
Photoelectric conversion element, 11... Indicator, 12...
...Support body, 13...Hematocrit support cylinder,
14...Hematocrit tube, 16...Slit, 17, 18a, 18b...Through hole, 19.
...Gear, 20...Motor, 21...
... Sector gear, 24 ... Stop part, 25 ...
...Square plate, 26a, 26b...Synchronization hole, 2
7... Arm, 28..."shaft, 30, 34... Cam, 31... Support box, 32... Hematocut support, 35, 46, 52, 65・・・・・・・・・
Amplifier, 36, 43, 53, 52, 62... Switch circuit, 37, 56... Detector, 38, 57...
... Integrating circuit, 39, 58... Logarithmic amplifier, 40,
47... Synchronous switch circuit, 41, 44, 63, 64.
...Hold circuit, 42,50...Differential amplifier, 45,54,55...Attenuator, 60...
...Comparison circuit, 61...Reference voltage circuit. Figure 1 Figure 2 Figure 3 Figure 4 Figure 5 Figure 6 Figure 7 Figure 8 Figure 9 Figure 10

Claims (1)

[Scope of Claims] 1. A jaundice meter that uses measurement light at the specific absorption wavelength of bilirubin and hemolysis supplementary light at a wavelength for correcting the absorption of hemoglobin in the measurement light, in which distilled water, a standard calibration material, and a subject are used. a synchronous switching mechanism for synchronously moving a data storage body containing a measurement sample, a filter element for obtaining light of the two wavelengths, and the data storage body; measurement comprising a photoelectric conversion element for converting an optical signal into an electrical signal, and means for obtaining a bilirubin signal corresponding to the optical signal of the measurement light and a hemolysis correction signal corresponding to the optical signal of the hemolysis correction light. and the bilirubin signal when the distilled water is on the optical path or the hemolysis correction signal when the distilled water is on the optical path as a reference. An automatic zero correction circuit that automatically controls the level by comparing it with the other level so that the difference becomes zero, or compares both signals with a constant voltage and automatically controls the difference so that the difference becomes zero, and a standard A jaundice meter characterized by comprising a standard calibration circuit that adjusts the indicated value of the indicator to a numerical value (standard value) determined as a standard calibration body when the calibration body is on the optical path. 2. In a jaundice meter that uses measurement light at the specific absorption wavelength of bilirubin and hemolysis supplementary light at a wavelength for correcting the absorption of hemoglobin in the measurement light, distilled water, a standard calibration material, and a specimen to be measured are used. A synchronization switching mechanism moves the stored data storage body, a filter element for obtaining light of the two wavelengths, and the data storage body in synchronization, and an optical signal obtained in synchronization with the movement of the filter element is electrically transmitted. A bilirubin signal corresponding to the optical signal of the measurement light, a bilirubin signal corresponding to the optical signal of the hemolysis correction light, and a hemolysis correction corresponding to the optical signal of the hemolysis correction signal, which includes a photoelectric conversion element that converts into signals. a measuring electric circuit comprising means for obtaining a signal; and either the bilirubin signal when the distilled water is on the optical path or the hemolysis correction signal when the distilled water is on the optical path. Automatically control the level of one of the two signals as a reference and compare it with the other level so that the difference becomes zero, or compare both of the signals with a constant voltage and automatically control so that the difference becomes zero. An automatic zero correction circuit to control, a standard calibration circuit that adjusts the indicated value of the indicator to a numerical value (standard value) determined as the standard calibration object when the standard calibration object is on the optical path, and The level of the hemolysis correction signal when the hemolysis correction signal is on the optical path and/or the level of the bilirubin signal when the specimen to be measured is on the optical path is determined by the hemoglobin in the measurement light and the hemolysis replenishment light. A jaundice meter characterized by comprising: a circuit for correcting by a correction coefficient determined by the ratio of absorption coefficients of the jaundice meter.