JPS585631A - Spectrochemical analysis device - Google Patents

Abstract

PURPOSE:To improve measurement operating efficiency by obtaining time division monochromatic light by using a high speed rotary body, introducing the light to a body to be checked, computing the light signal from the body to be checked at a high speed, and performing the determination of a plurality of oxidation reduced coloring matters and the like in a living organism simultaneously and in time series basis. CONSTITUTION:A tubular part 23 surrounding a light source 20 having a specified wavelength is provided. The high speed rotary body 22 having a slit 30 is provided on said part 23. Around the part 23 of the rotary body 22, a plurality of interference filters 37 for measuring the light having at least two wavelengths are provided at a specified interval. The irradiated light from the slit 30 at the tiem of rotation is divided into monochromatic light by each filter 37 in the time domain. Each monochromatic light is introduced into the body to be checked 41 through each light emitting transmission path 39. The light signal from the body to be checked 41 is introduced into a photoelectric element 43 through a light receiving transmissin path 42. The output signal from the element 43 is digitized 45 and stored in an electronic computer 46. The stored signal is computed and processed and the data in the time series basis are obtained.

Description

DETAILED DESCRIPTION OF THE INVENTION The present invention relates to a spectrophotometric analyzer for analyzing specimens such as living tissues of animals and plants by spectrophotometry. This paper relates to improvements to spectroscopic analyzers for analyzing effects at the cellular level.

In general, it is known that in vivo redox pigments, such as mitochondrial cytochromes, which are respiratory pigments, exhibit significantly different absorption spectra in their oxidized and reduced forms. By performing its detection and quantification, it is possible to obtain biological information at the cellular level.

By the way, as a means of obtaining this kind of biological information accurately,
Conventionally, the Dual-wavelength photometry method has been adopted, but this dual-wavelength photometry method is useful for determining the maximum absorption wavelength of the target substance (the oxidized form and the reduced form of the target substance) when quantifying the European reduced dye mentioned above. wavelength with the largest absorption difference) and the reference wavelength (
The method is to measure the difference in absorption at two wavelengths, which are as close as possible to the absorption maximum wavelength (a wavelength where absorption does not vary between oxidized and reduced forms).

In this case, the effects caused by the turbidity of the sample are approximately equal at both wavelengths and cancel each other out, and by selecting both wavelengths so that the influence of redox of other dyes is small, it is possible to Quantification becomes extremely accurate.

A conventional spectroscopic analyzer to which such a two-wavelength optical method is applied is shown in FIG. 1. This device includes a light source 1 having a predetermined wavelength range, a first monochromator 3 that spectrally spectra the absorption maximum wavelength λ1 in the sample 2 from the light source 1, and a reference wavelength λ2 in the sample 2 from the light source 1. a second monochromator 4;
A vibrating mirror 5 that vibrates its mirror surface in order to alternately irradiate the sample Pr2 with two beams with different wavelengths emitted from two monochromators 6.4, and a photoelectric element that converts the light transmitted through the sample 2 into an electrical signal. 6, a chopper 7 which is directly connected to the vibrating mirror 5 and divides the output signal from the optical IE converter 6 into signals originating from λ1 and λ2, respectively; and a chopper 7 which amplifies the output signals separated by the chopper 7. control circuit 8m
, 8b, a differential amplifier 9 that detects the output difference from these control circuits 8m and 8b, and an output S of the armpit differential amplifier 9.
It is composed of a recorder 10 that records values over time.

In this type, the control circuits 8m and 8ba each have λ1. Variable gain amplifiers 11&,llb which amplify the input signal Sλl,8λ8 originating from the beam of λf to an appropriate level, and variable gain amplifiers 1ta, 1 for the purpose of removing noise and increasing sensitivity.
Integrators 12a and 12b that integrate the signal Sλ/1°SλI snow amplified by step 1b, and a sample hold circuit 15 that holds the outputs from these integrators 121 and 12b for a predetermined period of time.
1.1! It is composed of b.

Note that in order to simultaneously input the outputs from the control circuits 9m and 8b to the differential amplifier 9, the holding time of the sample-and-hold circuit a in the control circuit 81 is T1 as shown in FIG. On the other hand, the holding time of the temple hold circuit 16b in the control circuit 8b is T2.

However, in such a conventional spectrometer, two monochromators 6.4 are used to obtain the specific wavelengths λl and λ2 necessary for quantifying the specific component of the sample 2. The two monochromators 3 and 4 are indispensable, which increases the number of parts, and when quantifying other components in the sample 2, in order to obtain the specific wavelength necessary for the other components. , it becomes necessary to reset the monochromator 6.4 each time, and this work is troublesome,
The disadvantage is that the quantitative determination of multiple components cannot be carried out continuously, and the operational efficiency is poor. In addition, sample 2, such as mitochondria, is prepared by crushing organs, fractionation, extraction, purification, and storing them in a cuvette. In addition, only one point of the same sample 2 can be taken as data, and in order to obtain time-series data, many samples 2 with certain conditions are required, so it is necessary to create sample 2 accordingly. Not only does the cost of materials increase, but also the material management is extremely difficult, as it is necessary to obtain materials with accurate conditions in order to create Sample 2, each of which has certain conditions. there were. Furthermore, in the conventional example, the switching speed of the two-wave moxibustion applied to the sample 2 is derived exclusively from the swinging speed of the vibrating mirror 5, but the vibrating mirror 5 Because it reciprocates via a mechanical rocking mechanism (not shown),
There is a limit to the oscillating speed of the vibrating mirror, making it difficult to increase the switching speed of the two wavelengths irradiated onto the sample 2. As a result, it was not possible to increase the transmission speed of each signal input from sample 2 to the control circuit 9ae8b, and it was not possible to analyze temporal changes within sample 2 in a short period of time. .

Furthermore, a control circuit 8m that processes the signal from the photoelectric element 6
, 85, the noise is removed by the integrators 12a and 12b and the signals are synthesized as shown in FIG. ), output 1
! The control circuit 9a is stupid, lacking in reliability and inferior in accuracy.

Since the system was 8 ha in size and included an analog arithmetic unit, its response was relatively slow, causing a loss in the precision and responsiveness of the device as a whole.

The present invention has been made based on the above-mentioned viewpoints, and its object is to provide a cylindrical portion having a predetermined wavelength range, arranging nine optical gaps, and surrounding this light source. A high-speed rotating body having a cylindrical portion with a negative slit is provided, and a plurality of interference filters for at least two-wavelength photometry are arranged at predetermined intervals around the cylindrical portion of the high-speed rotating body, and
The valley interference filter time-divisions the light irradiated from the slit as the high-speed rotating body rotates into monochromatic lights, guides each of these monochromatic lights to the test object through the light projection transmission path, and converts the optical signal from the test object. The light is guided to the photoelectric element through the receiving transmission line,
By digitizing the output signal from this photoelectric element at high speed, storing it in an electronic computer, and performing arithmetic processing based on this stored signal to obtain time-series data, it is no longer necessary to prepare a sample as before. In addition to making it possible to quantify multiple in-vivo redox dyes, etc. simultaneously and in chronological order, and to improve the measurement accuracy and shorten the measurement work time in quantifying the in-vivo redox dyes, etc. We are in the business of providing nine spectroscopic analyzers that can be used to improve the image quality.

Hereinafter, the present invention will be described in detail based on embodiments shown in the accompanying drawings.

FIG. 4 is a block diagram showing an embodiment of the spectroscopic analyzer according to the present invention.

In this embodiment, the light source 20 is made of, for example, a xenon lamp having a wide wavelength range from the infrared region to the external wavelength region. It is placed in the middle of the day. The light source 20 is equipped with a 500W stabilized power source, and an arc stabilizer is added to this to suppress fluctuations in the amount of light as much as possible.

Further, a high-speed rotating body 22 is disposed within the storage case 21, and as shown in FIGS. 4 and 885, this high-speed rotating body 22 is a cylinder that surrounds the light source 20 and closes the top and bottom It has a cylindrical portion 23, and a shaft 24 that extends downward from the stile, approximately at the center of the lower wall of this cylindrical portion. The shaft 24 is supported through the lower wall of the storage case 21 through a ball bearing 25, and the lower layer of the shaft 24 is connected to a pair of pulleys 27.
a.

27b and these pulleys 27m, 27b, and is connected to the shaft 7) 29m of a motor 29 via a power transmission device 26 consisting of a nine belt 28. Therefore, the high-speed rotating body 22 can rotate at a high speed of, for example, 33 Hz with the shaft 24 as the rotation axis in accordance with the rotation speed of the motor 29. Furthermore, an enlarged slit 60 is provided below the cylindrical portion 26 of the upper high-speed rotating body 22. Incidentally, an insertion hole 62 for passing a lead wire 61 to the light source 20 is formed in the upper wall of the cylindrical portion 26, and the lead 131 passes through the earthen wall of the storage case 21 and is connected to the power source. It is connected. A covering tube 36 that surrounds the upper half of the cylindrical portion 26 of the high-speed rotating body 22 is fixed to the long surface of the earthen wall of the storage case 21, and the light source 20 disposed inside the cylindrical portion 25 stabilizes the amount of light.

Furthermore, on the circumferential wall of the storage case 210, at positions corresponding to the slits 0 of the cylindrical portion 26, as shown in FIGS. 4 and 5, a plurality of holes are provided at equal intervals along the circumference. Transmission holes 64 are opened, and light guide pipes 5 protruding outward from the storage case 210 are provided corresponding to each transmission hole 4.

A lens for condensing light is inserted into each of the light guide tubes 65, and an interference filter 7 that transmits only monochromatic light of a predetermined wavelength is detachably attached to the outer part of the lens 6. It can be inserted easily. In this embodiment, six transmission holes 4 are provided, and each transmission hole 4 is equipped with interference filters 7a to 37f for two-wavelength photometry, which are necessary for quantifying in vivo oxidation-reduction complete dye tubes. For example, the interference filters 37 & 57b inserted therein are for extracting the reference wavelength λmm-605n and absorption maximum wavelength λb = 630 nm necessary for quantifying cytochrome aas, and the interference filters 67C1 and 7dt -! , reference wavelength λC-5 necessary for quantifying cytochrome b
The interference filters; 67@, ; 67f are for extracting the reference wavelength λe m 550 nm and the absorption maximum wavelength λf -54 necessary for quantifying cytochrome C.
This is for extracting 0ns. Each of the interference filters 67 is formed of a non-metallic thin film to have a half-width of four or less tones in order to keep its transmittance constant. Note that a through hole 8 is provided in the peripheral wall of the storage case 21 to clarify the arrangement of each interference filter 37.
The light from the light source 2o is taken out as an instruction signal 1 through the above-mentioned sulin 50 every time the high-speed rotating body 22 makes one revolution, and a synchronization signal is given to a computer 46 to be described later. It has become.

Further, in this embodiment, each interference filter 7a to 6
7f, as shown in Fig. 4 and #16 Fig.
The groups f are combined respectively and these lights 7' are grouped into groups 9a through 9f in Figures 4 and 6.
As shown in the figure, by fixing the middle part with fixed gold ^40p, they are warmed together and extend as one piece, and each party 7aipa5? The tips m to 59f are randomly arranged on the same plane. And each party 7 Aipa 69a
~! ? The f group is configured as a light projection transmission line 9 that guides the monochromatic light transmitted through each interference filter 7 to the subject 41. On the other hand, the reflected light from the object 41 is transmitted to the light receiving transmission line 42.
The light reception and transmission line 42 is made up of a group of optical seven eyepers 42a, and one end is coupled to the photoelectric element 46. and,
As shown in FIG. 4 and FIG. 6 G-1, the optical 7 eyeper group 42a has a fixing fitting 55 near its tip along with the light 7 eyeper 9a to 9f constituting the light projection transmission line 69. Fixed, each optical 7 eyeper 42a O tip is connected to the above optical 7 eyeper 5? m to 6? They are arranged on the same plane as the tip of fO and are arranged randomly. Therefore, it is possible to secure a wide irradiation surface and light receiving surface for the subject 41, to equalize the amount of light irradiated to the subject 41, and to effectively use the reflected light from the subject 41. It is designed to receive light.

The photoelectric element 46 (comprised of an automatic converter, a photodiode, etc.) converts the reflected light from the light receiving transmission line 42 into an electric signal. In this embodiment, the photoelectric element 46 is 200nm, as shown in FIG.
It has wavelength characteristics that exhibit substantially constant sensitivity in the wavelength range from ss to 80 Ontn K.

44 is an amplifier with linear characteristics that amplifies the output signal from the photoelectric element 46 to an appropriate level.

45 is, for example, a 16-bit D converter that digitizes the output signal from the amplifier 44 at high speed.

46 is an electronic computer that stores the output signal from the D converter 45 and performs arithmetic processing while removing noise based on this stored signal. Time series data of values can be obtained.

Therefore, when quantifying in-vivo redox pigments in a subject 41 such as a perfused organ using the spectroscopic analyzer according to this embodiment, as shown in FIG.
and the light irradiation surface and light receiving surface of the light receiving transmission line 42 are connected to the test object 4.
A perfusion tube 47 is connected to the subject 41, and an oxygen electrode 50 for detecting the oxygen concentration in the perfusion tube 47 is provided on the perfusion tube 47.
0 is input into the electronic computer 46 through another channel,
The recorder 10 displays temporal changes in oxygen concentration.

In this state, the light from the light source 20 is transmitted through the slit 3 of the cylindrical portion 26 as the high-speed rotating body 22 rotates.
The irradiated light is irradiated radially from zero, and this irradiated light is spread and guided into each light guide tube '65 at fixed time intervals at extremely high speed.
The light passes through each interference filter 67 of P3 and is time-divided into each monochromatic light. At this time, an interference filter 67 is provided from each light guide tube.
According to the arrangement order of a to 7f, the monochromatic lights λa to λf are sequentially guided to the light projection transmission line 69. Therefore, monochromatic light of λa to λf is sequentially irradiated onto the subject 41 from the light irradiation surface of the light projection transmission line 69, and the subject 41 is irradiated with monochromatic light of λ1
The reflected light of λf to λf is guided to the light-receiving surface of the light-receiving transmission line 42, and the reflected light signal guided to the output end of the light-receiving transmission line 42 is converted into an electrical signal through the photoelectric element 46, and then is converted into an electric signal by the amplifier shrine. ) i! It is amplified to n level. The output waveforms at this time are pulse signals Sλa to S corresponding to each interference filter 67a to 37f, as shown in FIG.
It is expressed as λf, the vertical axis of which represents the amount of light of each reflected optical signal, and the horizontal axis of which represents the time axis. The output signal from the amplifier 44 is then digitized at high speed by a D converter 45. At this time, the D converter 45
As shown in FIG.
Fig. 1 θ (each point of aJ (indicated by X in the figure) is converted into a digital signal, and each digital signal is stored in the computer 46.
A pulse signal 82 corresponding to each interference filter 67m to 7f is generated by the instruction signal from the through hole 8 during 20 rotations.
m to SAI is detected.

In this hard-wired electronic computer box, first and second arithmetic processing are performed based on the above-mentioned storage signal.

First, as shown in Figure 10 (0)), a reference potential line (for example, 0.5V) 51 is set to determine the data portion based on each reflected light signal, and If the digital signals on the reference potential line 51 or higher are, for example, 5Ii or higher continuously, they are processed as data based on the reflected light signal. As a result, white noise in parts other than the data part based on the reflected light signal is also removed.
Accurate data values are calculated based on the data portion determined by the first calculation process. In other words, the number of effective digital signals for one reflected light signal is, for example, 16.
) (Ps to PI3), the first
As shown in Figure O (C), the points from PIh to P4 and the points from Ptah to Pxs both correspond to the rising edge and falling edge of the reflected optical signal, so the digital signal corresponding to these points Discard Pg to pH
The digital signal corresponding to the O point is used as valid data. Then, the above valid data Ps to P1g
The digital signals corresponding to the points are subjected to addition averaging, or geometric averaging, etc., to obtain data for one reflected light signal. Due to the curvature, white noise in the data portion based on the reflected light signal is also removed.

Data S of each reflected light signal Sλa to Sλf is calculated by performing such calculations on each reflected light signal Sλa to Sλf.
A' to srI are stored, and the nine operations described above are repeated, for example, 50 times, and each reflected optical signal is calculated at an arbitrary pitch such as 0.5 seconds or 1 second based on the data of Nire et al. Calculate average data Smu to By.

As a result, the above average data is obtained as Sm, Sm...8yj), Ss and Sa, 8Dj, sc
.

After the logarithmic difference between SF and Sm is calculated, the electronic needle counter 4
At the output terminal of 6, the curves 5B-8A, 5D-8c, and 5y-8 are outputted in arbitrary intervals such as 1 second or 1 second. In addition, if the subject 41 such as a perfused organ moves,
As the distance between the irradiation surface of the light emitting transmission line 39 or the light receiving surface of the light receiving transmission line 42 and the subject 41 changes, the optical path length in the spectrometer may change. In the computer 46,
Noise processing that cancels the movement of the object 41 may be performed.1For example, the optical path at that time is determined gradually in time series using a reference wavelength, and the light amount at a predetermined optical path length is calculated as a ratio to this. This allows the optical path length to be corrected.

These characteristic curves are, for example, as shown in FIG.
The curve 1 shows the redox change of cytochrome aaS, the curve 1tlBo-3c shows the redox change of cytochrome b, and the curve 2 shows the redox change of cytochrome CC1m for 5F-8i+. There is. According to these songs #I to Rin, in FIG. 9, the perfusion tube 47 is filled with nitrogen! It is understood that all cytochromes show a reduction pattern due to nitrogen N2 when administered, and it is understood that cytochrome aa3 in the beak changes significantly. Furthermore, as shown in FIG. 9', when cyanide EN is administered into the perfusion tube 47, each of the cytochromes shows a maximum reduction pattern, but it is understood that cytochrome b in particular changes significantly. Time-series redox changes in in vivo redox pigments are similar to time-series changes in drug metabolism in perfusion systems, and can be said to be extremely effective as biological information. Note that much of the noise in FIG. 11 is the pulsating flow noise of the perfusion pump (not shown) used in the perfusion system 49.

Next, a second embodiment shown in FIG. 12 will be described.

In this example, the basic configuration of the spectroscopic analyzer is almost the same as that in the first embodiment, except that the interference filter 67 is used to quantify cytochrome aa3 and cytochrome b. Interference filter 5 necessary for
7a, 7b and 67c.

Interference filter 37g (transmission wavelength 340n groove is arranged) for excitation of 87dO gourd.
2 is bifurcated, and one light reception transmission line 42b is directly coupled to the photoelectric element 46, as in the first embodiment,
The reflected light signal is input to an Ω converter 45 via an amplifier 44, while the other light receiving transmission line 42c is connected to an interference filter 52 for fluorescence selection (transmission wavelength 4
5G am) to a separate photoelectric element 46', and the fluorescent signal is coupled to the Ω converter 4 via an amplifier 44'.
5 on a separate channel. still,
In FIG. 12, reference numeral 56 denotes a gold plate for fixing the branch portion of the light receiving and transmitting line 42. As shown in FIG.

Therefore, according to this implementation flK, as shown in FIG. 11, in addition to obtaining time-series data of redox changes of cytochrome gas and cytochrome b, as in the first embodiment,
The fluorescence of the subject 41 based on nine lights transmitted through the interference filter 57g for fluorescence excitation is detected by the photoelectric element 4M' via the interference filter 52 for fluorescence selection, and this fluorescence signal line, Similar to the reflected signal shown in the -th real jIlfI,
After being digitized at high speed by the Ω converter 45, it is stored in an electronic computer 46, where it is subjected to arithmetic processing while removing noise, and is output as time series data.

This fluorescent property is derived from the pyridine nucleotides of the skeletal membrane and appears as shown by the curve ■ in the TLTU diagram. In the figure, it is understood that when ethyl alcohol EtOH is administered into the perfusion tube 47 as shown in Figure 9, the pyridine nucleotides in the cartilage exhibit a reduction pattern due to the ethyl alcohol EtO1.

In each of the above embodiments, the light source 20Fi uses a xenon lamp, but this is not necessarily defined. For example, in the first embodiment, a xenon lamp is used as the light source 20. A tungsten carbon dioxide lamp or the like may be used as long as it has a wavelength range, and the high-speed rotating body 22 is not limited to those shown in the above embodiments. If it is a rotating body with a cylindrical part surrounding the light source 20, the interference filter 7 may be an interference filter 7a to 67f necessary for quantifying cytochromes or an interference filter for fluorescence excitation. Filter 67gK@ is used to quantify other in-vivo redox pigments, such as FAD (7rabin adenine dinucleotide) as 7rabin protein (reference wavelength 456n, maximum absorption wavelength 50G), It can also be applied to a round cape (reference wavelength s 75 nm, maximum absorption wavelength 85 nm) for quantifying intracellular calcium concentration. Furthermore, the light emitting transmission line 2119 and the light receiving transmission line 42 do not necessarily have to be formed integrally, as shown in the embodiment.
! In addition, in the second embodiment described above, the interference filter 52 for fluorescence selection is provided in the light reception transmission line 42C, but it is not necessary to form it separately. For example, the interference filter 52 may be incorporated into the storage case 21 to simplify the device system.Furthermore, in the second embodiment,
Fluorescence photometry of the subject 41 is carried out using only the interference filter 52 of -. To perform dimming, for example, the light reception transmission line 42C is further branched as shown in FIG.
The reflected light signal is input to the D converter 45 via an amplifier 44'I on a separate channel, and the above-mentioned light reception and transmission is performed in the electronic calculator 8146. The light transmission line 42 receives the reflected light signal from the line 42d.
to remove it from the fluorescent signal from C, or,
The difference between the fluorescent light signal and the reflected light signal from the photoelectric elements 45' and 4M'' is detected through an optical differential element (not shown), and after amplifying the detected signal, it is input to the D converter 45 and converted into an electronic signal. The calculation process may be performed using a calculator of 46 yen.
Further, in each of the above embodiments, calculation processing is performed in the electronic computer 46 based on reflected light or fluorescence signals from the four objects 41, but in addition to this, for example, Of course, in the case where the light is transparent, the calculation process may be performed in the electronic computer 46 based on the transmitted light signal from the subject 41. In addition, in each of the above embodiments, the instruction signal accompanying the 220 rotations of the high-speed rotating body and the signal from the oxygen electrode 50 are input to the computer 46 through separate channels, but in addition to this, various signals such as temperature and humidity are input to the computer 46. There is no problem in inputting the conditions into the electronic computer 46 so that they can be monitored, and in each of the above embodiments, the spectroscopic analyzer according to the present invention is used to quantify the redox pigment in the living body. Although the case is explained above, the present invention is not limited to this, and it goes without saying that the present invention can be applied to spectroscopic analysis of biological tissues of animals and plants, and can also be applied to environmental and industrial measurements, etc. It's okay to do that.

As explained above, according to the spectroscopic analyzer according to the present invention, a high-speed rotating body having a cylindrical part surrounding a light source and having a - slit in the cylindrical part is provided, and this high-speed rotation A plurality of interference filters for at least two-liquid length dimming are arranged at predetermined intervals around the cylindrical part of the body, and
Each interference filter time-divides the light irradiated from the slit as the high-speed rotating body rotates into monochromatic light, guides each of these monochromatic lights to the object through the light projection transmission path, and reflects or transmits them from the object. An optical signal such as light is guided to a photoelectric element through a light receiving transmission line, and the output signal from the photoelectric element is digitized at high speed and stored in an electronic computer, and based on this stored signal, arithmetic processing is performed to obtain time series data. As a result, there is no need to prepare a sample as in the past.
Not only is it possible to quantify in-vivo redox pigments, etc. using optical signals directly from subjects such as organ cells, but it is also possible to quantify multiple in-vivo redox pigments, etc. simultaneously and in chronological order. The measurement operation efficiency can be greatly improved. As a result, we can obtain extremely important biological information for the study of time-series changes in drug, ischemia, and hormone metabolism in perfusion systems, and we can also obtain spectroscopic information about a wide range of biological tissues in animals and plants. In addition, spectroscopic information on environmental and industrial measurements etc. can also be obtained. Further, according to the above-mentioned spectrometer, as the high-speed rotating body rotates at high speed, the light from the light source is time-divided into desired monochromatic light and guided to the subject, and the optical signal from the subject is digitized at high speed. Since arithmetic processing is performed using an electronic computer, delicate biological information can be obtained in a short time when quantifying in-vivo redox pigments, etc., and the measurement work time can be shortened. Furthermore, after the above-mentioned spectral separation, the oscillating mirror, which causes noise in the conventional method, is not needed, so the accuracy of the entire device can be greatly improved. It gets thicker.

[Brief explanation of the drawing]

FIG. 1 is a block diagram showing an example of a conventional spectroscopic analyzer.
FIG. 2 is a circuit diagram showing a specific configuration of the control circuit, FIG. 3 is a graph showing data processing means by the control circuit, and FIG. 4 is a block diagram showing an embodiment of the spectroscopic analyzer according to the present invention. Figure 5 is a partial cross-sectional view showing the specific configuration of the spectroscopic means that time-divides the light from the light source into monochromatic light, Figure 6 (top) is a cross-sectional view taken along the line A in Figure 4, and Figure 6 (b). is a cross-sectional view taken along line B-B in Figure 4, Figure 6 f-1 is a cross-sectional view taken along line C-C41 in Figure 4, Figure 7 is a graph showing the wavelength characteristics of a photoelectric element, and Figure 8 is a perfusion system. FIG. 9 is a graph showing the output signal from the amplifier, FIG. 1O (A) is a graph showing the operation of the D converter, and FIG. Figure 10(C) is a graph showing the second calculation process in the electronic computer, Figure 11 is a graph showing the output waveform from the computer, and Figure 12 is a graph showing the spectroscopic analysis device according to the present invention. A block diagram showing another embodiment,
FIG. 13 is a block diagram showing a modification of the spectroscopic analyzer according to the present invention. 1.20-...Light source 21...Storage case 2
2... High-speed rotating body 23... Cylindrical part (cylindrical part 60... Slit 34... Transmission hole 37
(ru7&～ayg')...Interference filter'! I9
... Light emitting transmission line 9a to δ9f... Optical 7 eyeper 42... Light receiving transmission line 42 &... Optical 7 eyer 46... Photoelectric element 44... Multiplier 45.
...AD transfer device 46...electronic computer 52...
Interference filter for fluorescence selection Patent applicant: Masaru Hui Mei Procedural Amendment January 6, 1980 Director General of the Japan Patent Office Haruki Shimada 1, Indication of the case 1981 Husu Petition No. 10102 H, Issued @O Name Spectroscopy Analytical Correspondence 3, Relationship with the Amended Person Case Patent Applicant Address 4-1-11-2034 Sakurajosui, Setagaya-ku, Tokyo
, Agent 108 Telephone 11580-Ji9311
8 Contents of the amendment Jl1 Paper ■) In the 6th line of page 8 of the specification, the word “light gap” was replaced with “light source”
I am corrected. 2) In the 20th line of the same page of the same book, the phrase "in-vivo-coordinated reduced dye" is corrected to "in-vivo-coordinated reduced dye." 3) In the 6th line of 21ji of the same book, “Fork is branched.”
I corrected the statement to ``branch into two prongs''.

Claims (1)

[Claims] l) A high-speed rotating body comprising a light source with a predetermined wavelength range, a round cylindrical part surrounding the light source, and a - slit in the cylindrical part; a plurality of interference filters that are arranged at predetermined intervals around the cylindrical portion of the rotating body and time-divide the light emitted from the slit as the high-speed rotating body rotates into at least monochromatic light for two-wavelength photometry; and,
A light emitting transmission line that is coupled to each interference filter and guides the monochromatic light from each interference filter to the subject, a light receiving transmission line that receives and guides the optical signal from the subject, and a light receiving transmission line that receives and guides the optical signal from the subject. A spectroscopic analysis device that has a photoelectric element that converts a signal into an electrical signal, and an electronic computer that digitizes and stores the output signal from the charging element at high speed, performs arithmetic processing based on this stored signal, and outputs time-series data. 2) Each interference filter has a through hole in the peripheral wall of the storage case that houses the light source and the high-speed rotating body, and is removably attached to the through hole. spectrometer. 3) The interference filter includes an interference filter for fluorescence excitation, and is configured to guide the fluorescence of the subject based on the light transmitted through the interference filter to the photoelectric element via the interference filter for fluorescence selection. A spectroscopic analysis device according to claim 1 or 2, characterized in that: 4) Both the light emitting transmission line and the light receiving transmission line are composed of a group of optical fibers, and the respective optical fibers are mixed with each other at least near their tips, and their tips are arranged on the same plane. A spectroscopic analyzer according to any one of claims 1 to 3, characterized in that: