JPS63275327A - Diagnostic apparatus - Google Patents

Abstract

PURPOSE:To obtain a highly accurate diagnostic result, in a diagnostic apparatus for measuring the amount of oxygen in an intracorporeal organ, by controlling the output powers of a plurality of light sources and the transmissivity of a filter by a light source control means and a filter driving means. CONSTITUTION:A light source control apparatus 2 automatically controls the output powers of light sources LD1-LD4 on the basis of the indication of a computer system 3 so that the transmission quantity of near infrared rays detected by a transmitted light detection apparatus 4 becomes optimum regardless of a wavelength. The filter driver 6 of the transmitted light detection apparatus 4 variably controls the transmissivity of a filter 5 on the basis of the indication of the computer system 3. The filter 5 is an annular ND one and transmissivity gradually changes around the circumference thereof and the filter 5 is rotationally driven by the filter driver 6. Even when the length (l) of a head part 60 changes at every examinee, the computer system 3 rotates the filter driver 6 by predetermined quantity and positions the filter 5 so that the transmissivity on an optical axis gives the optimum transmission quantity data.

Description

DETAILED DESCRIPTION OF THE INVENTION [Field of Industrial Application] The present invention relates to a diagnostic device for measuring the amount of oxygen in body organs such as brain tissue of humans or animals, and in particular, the amount of oxygen in hemoglobin in blood, ! The present invention relates to a diagnostic device that measures the amount of oxygen in internal organs by detecting the amount of oxygen in cytochromes within the body using near-infrared light.

[Conventional technology]

Generally, when diagnosing the function of internal organs such as brain tissue,
Whether the amount of oxygen in the body's organs is sufficient and properly utilized is a fundamental and important parameter.The supply of sufficient oxygen to the body's organs is critical to the viability of the fetus and newborn. This is essential, and if the supply of oxygen is insufficient, the mortality rate of fetuses and newborns is high, and even if they survive, the aftereffects will have a large impact on internal organs. All organs in the body are affected, but brain tissue is particularly damaged.

In order to quickly and easily diagnose the oxygen levels in internal organs, a diagnostic device as disclosed in U.S. Pat. No. 4,281,645, issued on August 4, 1981, has been developed. ing. This type of diagnostic device detects oxygen in internal organs, especially the brain, based on near-infrared absorption spectra of hemoglobin, an oxygen transport medium in the blood, and cytochrome a and a3 in cells that perform redox reactions. It is designed to measure changes in quantity. That is, near-infrared light with a wavelength range of 700 to 1300 nm has different absorption spectra αHb02 for hemoglobin bound with oxygen (Hb02) and hemoglobin from which oxygen has been removed (Hb), as shown in FIG. 4(a). '' Hb is shown, and Figure 4 (b
) as shown in oxidized cytochrome a, a3 (C
y02) and reduced cytochrome a, a3 (Cy
). Utilizing these properties of near-infrared light, four different wavelengths λ1, λ2, λ3, λ4 (e.g. 775nm, 800nm, 825nm, 850nm)
By time-divisionally injecting near-infrared light of , i.e., the respective concentrations of oxygen-bound hemoglobin (HbO2), deoxygenated hemoglobin (Hb), oxidized cytochrome a*a3 (Cy O2) + reduced cytochrome a, a3 (Cy). The amount of change is calculated, and based on this, for example, changes in the amount of oxygen in the brain are measured.

FIG. 5 is a schematic configuration diagram of such a diagnostic device. Fifth
In the figure, the conventional diagnostic device uses four different wavelengths λ1.
．． λ2. λ3. Light sources LD1 to LD4 such as laser diodes that each output near-infrared light of λ4, and light source LD
A light source control bag that controls the output timing of I to LD4!
55, and an optical fiber 50 for irradiating the head 60 with near-infrared light output from the light sources LDI to LDd, respectively.
-1 to 50-4 and optical fibers 50-1 to 50-4
an irradiation-side fixture 51 that bundles and holds the ends of the
Head 6 on the opposite side to the side on which the irradiation fixture 51 is attached
0, an optical fiber 53 that is held by the detection side fixture 52 and guides the near-infrared light transmitted through the head 60, and a near-infrared light guided by the optical fiber 53. A transmitted light detection device 54 that counts the number of photons of light and measures the amount of near-infrared light transmitted, controls the entire diagnostic device, and further measures the amount of oxygen change in the brain tissue based on the amount of near-infrared light transmitted. It consists of a computer system 56.

The computer system 56 includes a processor 62, a memory 63, and an output device M6 such as a display and a printer.
4 and an input device 65 such as a keyboard,
These are connected to each other by a system bus 66. Also, the system bus 66 of the computer system 56
A light source control bag W55 and a transmitted light detection device 54 are connected as the external I10.

The light source control device 55 drives the light sources LD1 to LD4 using drive signals ACT1 to ACT4 as shown in FIGS. 6(a) to 6(d) according to instructions from the computer system 56. In FIGS. 6(a) to 6(d), one measurement period Mk (k=1.2..old..) consists of N cycles CYI to CYN. Phase φn1 of any cycle CYn among cycles CYI to CYN
In this case, none of the light sources LDI to LD1 is driven,
The head 60 is not irradiated with near-infrared light from the light sources LDI to LD4, and in phase φn2, the light source LDI is driven and near-infrared light of, for example, 775 nm is output from the light source LDI. Similarly, in phase φn3, the light source LD2 is driven and near-infrared light of, for example, 800 nm is output from the light source LD2, and in phase φn4, the light source LD3 is driven and near-infrared light of, for example, 825 nm is output from the light source LD3. In phase φn5, the light source LD4 is driven and near-infrared light of, for example, 850 nm is output from the light source LD4.

Like this light source control device! ! 55 is configured to sequentially drive the light sources LDI to LD4 in a time-division manner.

The transmitted light detection device 54 also includes a filter 57 that adjusts the amount of near-infrared light from the optical fiber 53, and a lens 70.7.
1, a photomultiplier tube 58 that converts the light from the filter 57 into a pulse current and outputs it, an amplifier 59 that amplifies the pulse current from the photomultiplier tube 58, and a predetermined pulse current from the amplifier 59. a pulse height discriminator 60 that removes pulse currents below a pulse height threshold; a multi-thousand channel photon counter 61 that detects the photon frequency for each channel; and a detection controller 67, for example, that controls the detection period of the multi-channel photon counter 61. and a temperature controller 68 that adjusts the temperature of a cooler 69 housing the photomultiplier tube 58.

In a diagnostic device having such a configuration, when in use, the irradiation-side fixture 51 and the detection-side fixture 52 are firmly attached to predetermined positions on the head 60 with tape or the like.Then, the light source control device 1! LD4 is shown in Figure 6 (
When driven as shown in a) to (d), the light source LD
Four types of near-infrared light of different wavelengths are sequentially output from I to LD4 in a time-division manner, and are connected to optical fibers 50-1 to 50-.
Since the bones and soft tissues of the head 60 are transparent to near-infrared light, the near-infrared light mainly enters the head 60 through hemoglobin and cells in the blood. cytochrome a in
, a3 is partially absorbed and output to the optical fiber 53,
The transmitted light is added to the transmitted light detection device 54 from the optical fiber 53 . Note that in phase φn1 in which none of the light sources LDI to LD4 is driven, no transmitted light from the light sources LDI to LDJ enters the transmitted light detection device 54, and at this time, dark light is detected in the transmitted light detection device 54. .

The photomultiplier tube 58 of the transmitted light detection device 54 is for photon counting, which operates with high sensitivity and high response speed. The output pulse current of the photomultiplier tube 58 is transmitted to the amplifier 59.
The signal is input to the pulse height discriminator 60 via the pulse height discriminator 60. The pulse height discriminator 60 removes noise components below a predetermined pulse height threshold and inputs only signal pulses to the multichannel photon counter 61. The multi-channel photon counter 61 operates in accordance with a control signal CTL as shown in FIG. 6(e) from the detection controller 67.
) The drive signal ACT of the light sources LDI to LD4 as shown in
Period 'r synchronized with I to ACT4.

The number of photons detected for each wavelength of light incident from the optical fiber 53 is counted.

As a result, transmission amount data for each wavelength of near-infrared light is obtained.

That is, as shown in FIGS. 6(a) to 6(e), during one cycle CYn of the light source control device 55, the phase φn
1, since none of the light sources LDI to LD4 are driven, the transmitted light detection device 5-4 counts the dark light data d. In addition, in phases φn2 to φn5, the light source L
Since DI to LD4 are sequentially driven in a time-division manner, the transmitted light detection device 54 detects four different wavelengths λ1. λ2.
Transmission data of near-infrared light of λ3゜λ4 1. 1.

λ1 1. 1 is counted sequentially.

λ3 λ4 In this way, the dark light data d and the transmission amount data tai, which are sequentially Si numbered during one cycle CYn,
taz , t , t are N times sai λ3
Counting continues over λ4 cycles CYI to CYN. That is, with N cycles, one measurement period Mk (k
=1.2. ...). Specifically, for example, one cycle CY n is 200 μs and N is 10
000 times, one measurement period M is 2 seconds. At the end of one measurement period Mk, the dark light data axis counting result 1゛,Tyo2'Ta3'''A4A1 (=Σtλj/CYn) is transferred to the computer system n=1. It is stored in the memory 63.

The processor 62 performs the hair removal 63 in one measurement period Mk.
Transmission data and dark light data ('1') stored in
,'I','I',T,D)A
1 A2 A3 A4 ■ and M at the start of measurement. Transmission amount data, dark light data (Ta2'A21.T□3゜Ta4'
p) Dark subtraction is performed from MO, and then the rate of change of transmission I ΔT is 1. ΔT□2゜Δ′r, Δ”A
Calculate 4. That is, the rate of change in the amount of transmission λ3 ATAt, ATa2, ATa3.

A1゛Yo, ATa J =j Og[(T'a jD) Mk/
(T, -D) ] (J=1 to 4) λJ
MO...(1) Calculated as follows. Note that the reason why a logarithm is used in calculating ΔT is to represent a change in optical density.

The rate of change in the amount of transmission ΔT, Δ
From T, ΔT, ΔTλ4, A1 A2 A
3 Hemoglobin combined with oxygen (HbO2), deoxygenated hemoglobin (Hb), oxidized cytochrome a
, a (Cy02) + reduced cytochrome a, a
3 Concentration change of (Cy) ΔX1lb02'ΔX Δ
Detecting each of X ΔX 11blcy02
° cy, that is, the concentration change of each component ΔX1! ,. 2
゜ΔX is detected as ΔXl1b'ΔXcy02゛Cy (2). Here α1j is each wavelength λj (λ1
．． λ2. λ3. Each component 1 (HbO, Hb
, Cy02, Cy), and Figure 4(a)
, is predetermined from (b).

Further, 1 is the length of the head 60 in the direction in which near-infrared light travels.

The concentration change ΔX11 of each component detected in the computer system 56 in this way. . 2゜ΔX
In other words, ΔX is 11bIcy02 in the brain
cy Since this is a change in the amount of oxygen, by outputting these to the output device 64, it is possible to know and diagnose the change in the amount of oxygen in the brain.

[Problem that the invention seeks to solve]

Incidentally, the amount of near-infrared light transmitted varies significantly on the order of 10 to 105 depending on the size of the head 60, that is, the length 1 of the head 60 in the direction in which the near-infrared light travels. Furthermore, even if it is assumed that the size of the head 60 is constant regardless of the patient,
The output powers of the light sources LDI to LD4 (laser diodes) are at wavelengths λ1°λ2. λ31λ4 (775nm, 80
0. nm.

By changing on the order of 101 for each wavelength of 825 nm and 850 nm, the transmission amount of near-infrared light itself changes sequentially on the order of 101.

On the other hand, since the dynamic range of the photomultiplier tube 58 of the transmitted light detection device 54 is on the order of 102, the amount of light incident on the photomultiplier tube 58 during diagnosis does not depend on the length 1 of the head 60. In addition, it is desirable that the output power of the light sources LD1 to LD4 be kept approximately constant regardless of wavelength-dependent changes.

To this end, conventionally, a variable attenuation ND filter whose filter value can be manually adjusted is used as the filter 57, and when starting diagnosis of one patient, the amount of light incident on the photomultiplier tube 58 The filter value of the filter 57 and the output power of each of the light sources LDI to LD4 are manually adjusted so that the amount of transmission becomes optimal.

In this way, with conventional diagnostic equipment, it is necessary to manually adjust the filter 57 and the output power of the light sources LDI to LD4, making it impossible to quickly and accurately adjust the amount of transmission to the optimum value. There was a problem.

Furthermore, since the filter value of the filter 57 is not changed after being adjusted once at the start of diagnosis, even if the position of the filter 57 shifts during diagnosis, this cannot be recovered and the accuracy is reduced. There was a problem that high diagnostic results could not be obtained.

The present invention provides a diagnostic device that can quickly and accurately adjust the amount of near-infrared light transmitted so that the amount of transmitted near-infrared light is suitable for detection, and at the same time can obtain accurate diagnostic results. It is FI-like to do so.

[Means for solving problems]

The present invention includes a plurality of light sources that respectively output near-infrared light of different wavelengths, and a light source control means that controls the plurality of light sources and sequentially causes the near-infrared light output from the plurality of light sources to enter internal organs. , a diagnostic device comprising a transmission amount detection means for detecting near-infrared light transmitted through an internal organ, the transmission amount detection means comprising: a filter that attenuates the near-infrared light transmitted through an internal organ; filter driving means for variably setting a filter value of the plurality of light sources, and the light source control means and the filter driving means adjust the output power of the plurality of light sources so that the amount of transmitted near-infrared light is a light amount suitable for detection. The present invention attempts to improve the problems of the prior art described above by providing a diagnostic device characterized in that the filter values of the filters are controlled respectively.

[Effect]

In the present invention, prior to actual measurement of the amount of oxygen in internal organs,
The filter value of the filter of the transmitted light detection means and the output power of the plurality of light sources are controlled so that the near-infrared light transmitted from the internal organs becomes a light amount suitable for detection.

For this purpose, multiple light sources are sequentially driven to make near-infrared light with different wavelengths enter the internal organs one after another.The amount of near-infrared light that has passed through the internal organs is detected by a transmitted amount detection means. Then, the output power of each of the plurality of light sources and the filter value of the filter are determined so that the amount of transmission becomes 1 & appropriate.

After determining the filter value of the filter and the output power of the light source so that the amount of transmitted near-infrared light becomes a light amount suitable for detection, actual diagnosis is performed.

In actual diagnosis, when driving multiple light sources in sequence,
The filter value and the output power of the light source are set to the filter value and output power obtained as described above, and then near-infrared light with different wavelengths is sequentially incident on the internal organs to detect the internal organs. Measure the amount of oxygen.

〔Example〕

Embodiments of the present invention will be described below based on the drawings.

FIG. 1 is a schematic diagram of an embodiment of a diagnostic device according to the present invention. In FIG. 1, the same parts as in FIG. 5 are designated by the same reference numerals, and the explanation thereof will be omitted.

The light source control device 2 of the diagnostic device 1 shown in FIG. λ2. λ3. λ
The output powers of the light sources LDI to LD4 are automatically controlled in accordance with instructions from the computer system 3 so that the output powers of the light sources LDI to LD4 are not dependent on the power of the light sources LDI to LD4.

Also, transmitted light detector r! The 14 filter drivers 6 variably control the filter value of the filter according to instructions from the computer system 3, so that even if the size of the head 60, that is, the length 1 differs from patient to patient, the photomultiplier tube 58 This ensures that there is no variation in the amount of light incident on the lens.

The computer system 3, like the conventional computer system 56, includes a system bus 11, a processor 7, a memory 8. Output device 9 and input device r! 110 is connected, the light source control device 2 is controlled to automatically adjust the output power of the light sources LDI to LD4,
The filter driver 6 is controlled to automatically adjust the filter value of the filter 5.

The operation of the diagnostic device having such a configuration will be described next.

At the beginning of measurement rgF5 Mo, one cycle CYn
In the phases φn2 to φn5, the light sources LD1 to LD
4 are driven sequentially in a time-division manner, and in the transmitted light detection device 4, the 4
Two different wavelengths λ1. λ2゜λ3. Transmission amount data t, 1 of near-infrared light of λ4.

, t are counted sequentially. Transmission amount data 1 . 1. 1λ1 λ2 λ3
"Then, counting is performed over N cycles CYλ4 1 to CYN of Mo at the start of measurement, and when the Nth cycle CYN is completed, the counting results (T, T
, T , T ) is con λ1 λ
2 λ3 λ4 MO° Transferred to the computer system 3 and stored in the memory 8.

In this way, M at the start of measurement. Based on the transmission amount data (T, T, 2.T, 3゜λ1 Tλ4) MO stored in the memory 8, the processor 7 determines whether each of these transmission amount data 'r to Tλ4 is the optimum value λ1. to judge. Also, each transparent I data T.

It is determined whether Tλ4 is different for each wavelength.

When determining that the transmission amount data T to TA4 are not optimal, the computer system 3 drives the filter driver 6 to change the filter value of the filter 5 by a predetermined amount, and at the same time changes the output power of the light sources LDl to LD4. is changed by a predetermined amount.

In addition, if the weekly excess data T□1 to T□4 are different for each wavelength, the filter value of the filter 5 and the light source LDI to L
The output power of D4 is changed for each wavelength. The optimum filter value for each wavelength and the output power of the light sources LDI to LD4 thus determined are stored in the memory 8.

M at the start of measurement. As described above, the optimal filter value for each wavelength and the output power of the light sources LDI to LD4 stored in the memory 8 are the same as the filter value of the filter 5 and the output power of the light sources LDI to LD4 during actual measurement of the amount of oxygen. Used to automatically control power.

That is, one subsequent measurement period M, (k=1.2°...
), the phase φ of one cycle CYn
When measuring the transmission amount data T1 to TA4 at n2 to φn5, the processor 7 calculates the filter value of the filter 5 and the light sources LDI to LD based on the filter value and output power for each phase stored in the memory 8.
Change the output power of 4. In this way, the amount of oxygen in the brain can be measured by automatically and sequentially changing the filter value of the filter 5 and the output power of each of the light sources LDI to LD4 so that the amount of transmission becomes optimal.

FIG. 2 is a diagram showing a configuration example of the filter 5 and filter driver 6 shown in FIG. 1.

In FIG. 2, the filter 5-1 is an annular ND filter, and the filter value gradually changes along its circumference. The filter 5-1 is rotatably driven by the motor 6-1, and when the portion PS1 with the largest filter value is positioned on the optical axis, near-infrared light incident on the photomultiplier tube 58 is While the amount of light attenuation becomes maximum, when the portion PS2 with the smallest filter value is positioned on the optical axis, the amount of light attenuation of the near-infrared light incident on the photomultiplier tube 58 becomes the minimum. The fine motor 6-1 is, for example, a pulse motor, and is controlled by the computer system 3.

Filter 5-1 and motor 6-1 as shown in FIG.
According to this configuration, even if the length 1 of the head 60 changes from patient to patient, the computer system 3 can control the motor 6 as described above.
-1 by a predetermined amount, rotate filter 5-1,
The filter 5-1 can be positioned so that the filter value on the optical axis provides optimal transmission amount data.

In this way, the filter values can be automatically set without manual operation, and the operability during diagnosis can be significantly improved.

However, in the above example, since the filter 5-1 is mechanically rotated by the motor 6-1, the positioning accuracy of the filter 5-1 deteriorates when used for a long time.
The reliability of diagnostic data may decrease. Further, since mechanical parts are used, it is not suitable for downsizing the diagnostic device, and furthermore, the motor row 1 has the drawback that it consumes a considerable amount of power.

FIG. 3 is a diagram showing a configuration example of a filter and a filter driver that can further improve the reliability of the diagnostic device and make it smaller.

In FIG. 3, the filter 5-2 consists of a liquid crystal plate. Since the liquid crystal plate has a light attenuation rate that changes depending on the applied voltage, this property can be used to make the filter value of the filter 5-2 variable.

A driving section 6-2 that applies an applied voltage to the filter 5-2 of the liquid crystal plate is connected to the filter 5-2. The drive unit 6-2 further includes a conversion unit 12 that converts a control signal from the computer system 3 into a filter value, and a drive circuit 13 that applies an applied voltage corresponding to the filter value converted in the conversion unit 12 to the filter 5-2. It consists of

The converter 12 converts the control signal from the computer system 3 into a filter value proportional to its magnitude, for example. In this case, the voltage applied to the filter 5-2 of the liquid crystal plate increases in proportion to the magnitude of the control signal from the computer system 3, and by changing the magnitude of the control signal in the computer system 3, the voltage applied to the filter 5-2 of the liquid crystal plate becomes larger. The light attenuation rate of 2 can be changed linearly. Furthermore, when the converter 12 nonlinearly converts the control signal from the computer system 3 into a filter value, the computer system 3 changes the magnitude of the control signal to adjust the light attenuation rate of the filter 5-2. It can be changed non-linearly.

When a liquid crystal plate is used as the filter 5-2 in this way, there is no need for a mechanically controlled part, so the reliability does not deteriorate even if the diagnostic device is used for a long time. It becomes possible to downsize the diagnostic device and reduce its power consumption.

Although the above embodiment has been described as having four light sources LDI to LD4, the number of light sources is not limited to four, and may be two or four or more.

〔Effect of the invention〕

As explained above, according to the present invention, the output powers of a plurality of light sources and the filter values of the filters are respectively controlled by the light source control means and the filter drive means, so that the size of internal organs can be adjusted for each patient. Even when the output power of multiple light sources is different, the filter value and output power can be quickly and accurately adjusted so that the amount of transmitted near-infrared light is suitable for detection, which improves accuracy. High diagnostic results can be obtained.

[Brief explanation of drawings]

FIG. 1 is a configuration diagram of an embodiment of a diagnostic device according to the present invention, and FIG.
The figure shows an example of the configuration of the filter and filter driver in FIG. 1, FIG. 3 shows another example of the configuration of the filter and filter driver in FIG. 1, and FIGS.
) are diagrams showing the absorption spectra of hemoglobin and ditochrome, respectively; Figure 5 is a configuration diagram of a conventional diagnostic ItIi device;
FIGS. 6(a) to 6(d) each show the drive signal A C'I
"The time chart of 1 to ACT4, and FIG. 6(e) is the time chart of the control signal CTL. 1...Diagnosis device, 2...-Light source control device, 3...Computer system, 4... Transmitted light detection device, 5.5
-1.5-2...Filter, 6...Filter driver, 6-1...Motor, 6-
2... Drive unit, LDI to LD4... Light source patent applicant Hamamatsu Potonics Co., Ltd. Agent Patent attorney
Masaharu Ueki PS2 Figure 3 Figure 4 λ1 Person 2 Person 3 λ4 Person 1 Person 3 Procedural Amendment (Ki) 7 1985 9JI031-(1 Display of Case 1988 Patent Application No. 110465 2 Title of Invention Diagnostic device 3 Relationship with the person making the amendment Patent applicant address 1126 Ichino-cho, Hamamatsu City, Shizuoka Prefecture Representative: Hamamatsu Photonics Co., Ltd. Address: Teruo Ma 4 Agent address (zip code: 140) Tokyo Parts Co., Ltd. Yoku Higashi Oi 3-chome 120-7-6 Target of amendment (1) “Claims” column of the specification ■, page 21, line 6, page 21, line 13 to special amso Ac=
rJ#/'l I W! 1 4ren1”l a*su1?
Contents of amendment (1) The claims are amended as shown in the attached sheet. (2) From page 2, line 19 to page 3, line 1 of the specification, “
``Internal organs'' is corrected to ``Object to be measured such as internal organs J.'' (3) Page 3, line 3 of the specification, page 15, line 8, 1
Page 5, line 14, page 15, line 16, page 15, line 18
Line 157'l Line 20 [1, Page 16, Line 3 [1
, page 16, line 11, page 16, line 16, page 16, line 17, page 17, line 1, page 17, line 8, page 25, line 5 to In the 6th line, ``near infrared light'' is corrected to ``electromagnetic waves''. (4) Specification page 3, line 3, page 15, line 16, page 15, line 17, page 15, lines 19 to 20, page 16, line 10, Page 16, line 11, page 16, line 16, page 16, line 17 Correct it to "object to be measured." (5) Specification S, page 14, line 9, page 14, line 13 l]
, page 15, line 2, page 16, line 1, page 16, line 5
line, page 16, line 13, page 16, line 20, 1st
Page 7, line 2 [1, page 17, line 5, page 17, line 6, page 18, line 5, page 18, lines 14 to 15, page 20, line 3 Lines to 4th line, page 20, line 8, page 20, line 11, page 20, line 14, page 20, line 16, page 21, line 3, 21 Page 4th line to 5th line Claims 51'S1 q+r day, Nu n41) Ln11 υ1
J-1, A14 5311-22, page 11, line 11, page 23, line 9, page 23, line 14, page 23, line 18
The words “filter value” at the beginning of lines 19 to 19 r1, page 24, line 5, page 25, line 2, and page 25, lines 6 to 7 are replaced with “transmittance”. correct. (6) In the specification, page 14, line 10 [1, page 18, line 6, page 22, line 5 ['', page 25, line 3, 1 patient'' is 1 subject name 1 I am corrected. (7) Meihan, page 24, line 18, line 1, and line 19, 1, between ``1'' and 19th line ``Furthermore, the electromagnetic waves from the light source are not limited to near-infrared light, but may also be far-infrared light, visible light, microwaves, etc.'' Furthermore, the diagnostic device of the present invention can be applied not only to the field of medical diagnosis but also to a broader field of diagnosis or measurement, and the diagnostic target is not limited to internal organs but also general measurement targets such as meat muscles. Insert "It can be a thing." 11 The light source of the wave device is exposed to the light source, and the multiple light sources are controlled, and one piece of green onion output from the multiple light sources is sequentially incident on one plate. In the diagnostic apparatus, the transmission amount detection means includes a light source control means for controlling the light source, and a transmission amount detection means for detecting the amount of m transmitted through the ship's dish 1. filter driving means for variably setting the summer light of the filter;
The light source control means and the filter driving means respectively control the output power of the plurality of light sources and the return power of the filter so that the amount of light transmitted on the windward side becomes a light amount suitable for detection. A diagnostic device characterized by:

Claims (1)

[Claims] 1) A plurality of light sources that output near-infrared light of different wavelengths, and controlling the plurality of light sources to sequentially make the near-infrared light output from the plurality of light sources enter internal organs. In a diagnostic device comprising a light source control means and a transmission amount detection means for detecting near-infrared light transmitted through the internal organs, the transmission amount detection means includes a filter that attenuates the near-infrared light transmitted through the internal organs. and,
filter driving means for variably setting a filter value of the filter, and the light source control means and the filter driving means control the plurality of light sources so that the amount of transmitted near-infrared light is a light amount suitable for detection. A diagnostic device characterized in that the output power and the filter value of the filter are controlled respectively. 2) The light source control means controls the output power of each of the plurality of light sources so that the amount of transmission detected by the transmission amount detection means is approximately constant regardless of the wavelength. A diagnostic device according to claim 1. 3) The filter is an annular ND filter whose filter value gradually changes along the circumference, and the filter driving means is a motor that rotates the annular ND filter by a predetermined amount. A diagnostic device according to claim 1. 4) The filter comprises a liquid crystal plate whose filter value changes depending on the applied voltage, and the filter driving means applies a predetermined applied voltage corresponding to a predetermined filter value to the filter of the liquid crystal plate. A diagnostic device according to claim 1, characterized in that: