JPH01101966A - Endoscopic spectral diagnostic apparatus - Google Patents

Abstract

PURPOSE:To obtain data effective for spectral diagnosis in real time, by displaying the chromaticity of a region to be measured on the basis of the output of a chromaticity measuring means. CONSTITUTION:An endoscopic spectral diagnostic apparatus 1 is constituted of an electronic scope 2, a light source apparatus 3 for supplying illumination light to said electronic scope 2, a signal processing apparatus 4 for performing the signal processing of the electronic scope 2 and a color monitor 5 displaying an image on the basis of the output signal of the signal processing apparatus 4. The chromaticity of an object is calculated by the chromaticity calculation circuit 34 of the signal processing apparatus 4 and the chromaticity thus calculated is superposed on an image signal through a superimposition circuit 33 to be displayed on the color monitor 5.

Description

DETAILED DESCRIPTION OF THE INVENTION [Industrial Application Field 1] The present invention relates to a transendoscopic spectroscopic diagnostic apparatus that performs spectroscopic diagnosis using an endoscope.

E. Prior Art] There have been many proposals for using data measured using an endoscope as an auxiliary means for diagnosis, and the use of spectral data is one of them. For example, in JP-A-61-107482, a semi-transparent mirror that directs white light to a predetermined position and passes reflected light from an illuminated object, and a universal filter that passes only a desired wavelength band of the reflected light. and a means for measuring the intensity of each part of a plurality of types of images by the plurality of wavelengths of light outputted from the unipernal filter, respectively, and a means for obtaining an intensity difference of each corresponding part of the plurality of types of images. An optical imaging device has been proposed. In this method, a plurality of images obtained from a universal filter are combined to enlarge the difference in intensity between a normal region and an abnormal region, thereby making it easier to identify the region.

On the other hand, JP-A-60-79251 discloses an image observation diagnostic device that attaches a light branching mirror to the tip of an endoscope, performs spectroscopic measurements of areas that cannot be viewed directly, processes the spectra, and performs spectroscopic analysis of objects. is suggesting.

[Problems to be Solved by the Invention] In the method disclosed in JP-A-61-170482, the spectral differences between the normal area and the abnormal area are selectively extracted using a universal filter, and the multiple images are superimposed to calculate the intensity difference. Although it is stated that it will be enlarged, there is no presentation of specific wavelength characteristics of the universal filter, and that selective wavelength images will be superimposed and displayed using computer processing, but this content is not specifically stated. In addition, although this publication discloses an example in which images are taken on film using selective wavelengths, in the field of medical diagnosis, the desired abnormal For doctors whose primary purpose is diagnosis, it is extremely troublesome to decide whether it is better to use a positive-positive film combination or a negative-positive film combination when recording images. be. Furthermore, under the light ω, which is not sufficient even for normal endoscopy, if a universal filter is used that only passes the desired wavelength range, and if a polarizing filter is also used, the amount of light is extremely large. In order to minimize the burden on patients, there are extremely few opportunities to take photographs during endoscopy, which is performed in a short clinical period. Also,
Although JP-A No. 60-79251 states that spectroscopic analysis of a subject is performed by processing spectra, there is no specific disclosure of providing high-quality data in real time.

The present invention was developed in view of the above circumstances, and its purpose is to provide a system with high accuracy that will serve as an effective auxiliary means for diagnosing lesions without imposing any special burden on both patients and doctors in clinical settings. An object of the present invention is to provide a transendoscope spectroscopic diagnostic device that provides high spectroscopic data.

[Means and effects for solving the problems 1 The present invention has the following features:
A spectroscopic measurement means for determining the chromaticity of the object to be examined is provided within the endoscope, so that the chromaticity of the object to be examined can be easily measured for spectroscopic diagnosis.

[Example] Hereinafter, the present invention will be specifically explained with reference to the drawings.

Figures 1 to 11 relate to the first embodiment of the present invention; Figure 1 is a block diagram of the first embodiment, Figure 2 is a front view of a one-rotation filter, and Figure 3 shows spectral tristimulus values. Fig. 4 is an explanatory diagram of the operation of the first embodiment, Fig. 5 is a configuration diagram of the chromaticity calculation circuit, Fig. 6 is an explanatory diagram of the processing process for performing spectral diagnosis, and Fig. 7 is an illustration of the same color chart. Figure 8 is a measurement diagram showing different color charts expressed on chromaticity coordinates, and Figure 9 shows that a large number of measurement results converge on a reference point. The explanatory diagram, FIG. 10, is a measurement diagram showing the measurement results of the normal part and the abnormal part, and FIG. 11 is a diagram in which more measurement data than that in FIG. 10 is plotted on the chromaticity diagram.

As shown in FIG. 1, the transendoscopic spectroscopic diagnostic apparatus 1 of the first embodiment includes an electronic scope 2, a light source device 3 that supplies illumination light to the electronic scope 2, and performs signal processing of the electronic scope 2. Signal handler! 1 device 4, and a color monitor 5 that displays an image based on the output signal of this signal processing device 4.

The electronic scope 2 has an elongated insertion portion so as to be inserted into a body cavity, etc. A light guide 7 formed of a fiber bundle is inserted into the insertion portion, and the incident end surface of the light guide 7 is connected to the light source device 3. By connecting to
Illumination light is supplied from the light source device @3.

In the light source device 3, white light from a white light lamp 9 such as a xenon lamp, which is turned on by power from a power source 8, is supplied as illumination light to the incident end surface of the light guide 7 through a rotary filter 12 that is rotationally driven by a motor 11.

As shown in FIG. 2, the rotating filter 12 includes spectral three-color transmitting filters 13R, 13G, and 13B for regular field sequential illumination. A tristimulus value generation color transmission filter (hereinafter referred to as a tristimulus value filter) 14x that generates transmitted light with a spectral characteristic of a stimulus value of 9.7.

14 ma, 147 is set.

The illumination light passing through the tristimulus value filter 14, i4y, 147 is designed to have spectral tristimulus value characteristics as shown in FIG.

The imaging using the frame-sequential light and the imaging using the tristimulus value light can be switched, for example, by a switch 15 provided on the operation panel on the front of the signal processing device 4.

The motor 11 is controlled by a motor driver 16 to rotate at a constant speed in synchronization with a timing signal output from a timing generator 17. Therefore, for the rotating filter 12 rotated at a constant speed,
Which filter 13I (1=R, G,
The position sensor 18 detects whether B) or 14i (i=x, y, Z) is interposed. For example, the timing at which the red transmission filter 13R ends being interposed in the optical path is detected by detecting the position of the hole 19a provided at the periphery of the rotary filter 12. Other filters 13G, 1
The position of filter 3B is determined by detecting this hole 19a, and is also determined for the other filter 141. Thus, in the normal case when the switch 15 is off, signals captured under the R, G, and B illumination lights that have passed through the color filter 131 are captured. On the other hand, when the switch 15 is turned on, signals captured under tristimulus value illumination light are captured.

By the way, the object illuminated by the tristimulus value light is a C0D lens placed on the focal plane of the object by the objective lens 21.
22, photoelectrically converted, and accumulated as charges. The drive signal is applied by the driver 23 via the signal cable, is read out, is input to the amplifier 24 in the signal processing device 4, and is amplified.
The signal is input to a process circuit 25, subjected to signal processing such as contour correction and aperture correction, and converted into a digital signal by an A/D converter 26. The first . Second. Third
Each frame is sequentially written into the memories 29a, 29b, and 29C. The data written in these memories 29a, 29b, and 29c are simultaneously read out, converted to analog signals via the D/A converter 31, and then sent to the encoder 3.
2, the signal is converted into an NTSC video signal and output to the color monitor 5 via the superimpose circuit 33.

Further, the analog color signal from the D/A converter 31 is input to a chromaticity calculation circuit 34, and the chromaticity calculation result is superimposed on the NTSG video signal via a superimpose 33 and output.

The color monitor 5 has a switch 15 turned on.

By turning it off, it is possible to select between color display of a subject image captured with normal R, G, and B plane sequential light and color display of a subject image captured with tristimulus value light as described below.

As the rotating filter 12 rotates, the subject appears as shown in Fig. 4 (a).
) k, as shown, R9 again, Go″9.B, τ.

Ro... are sequentially illuminated. However, position sensor 1
Based on the output of 8, at the end of each illumination light, the timing generator outputs the illumination period end pulse shown in FIG. It outputs a transfer pulse (see (C) in the same figure) that transfers the signal charge from the light receiving section) to the transfer section (in the case of a frame transfer type COD) or the vertical shift register (in the case of an interline type CCD). For example, when the switch 15 is off, an off signal is input to the driver 23, and by application of this off signal, the driver 23 selects the driving condition and selects the R2O, B
For the signal imaged by the illumination light, a readout clock consisting of a vertical transfer lock and a horizontal shift clock is applied to the transfer unit (or vertical shift register) as shown in FIG. 4(d), and this readout clock is The signal read by the first . Second. The data is written to the third memories 29a, 29b, and 29c.

On the other hand, the signal imaged under the R, y, 2 illumination light is swept out by applying a clock (at an extremely high frequency), as shown in FIG. 2(e).

(For example, the memories 29a, 29b, and 29G are held in read mode during this period.) Therefore, in this case, normal color display is performed.

On the other hand, when the switch 15 is turned on, for example, at tl, as shown in FIG. 9(f), FIG. 9(d) and (Q) are reversed. In other words, the signals positively imaged by the R, G, and B illumination lights are discarded, while the signals positively imaged by the colors of the x, y, and '2 illumination lights are discarded.
The imaged signals are written into memories 29a, 29b, and 29c.

Therefore, in this case, l1i under tristimulus value illumination light.
i! &The subject image is displayed in color. When the subject is displayed in color under this tristimulus illumination light,
For example, it is easier to display immunity to the test area on the Buddha seat map, improve the displayed spermatozoa on the Buddha seat chart, and determine whether the test area on the Buddha seat chart is normal or not. It is possible to perform spectroscopic diagnosis with high accuracy.

The functions of the above spectroscopic diagnosis will be explained below.

The chromaticity meter itching circuit 34 shown in FIG. 1, for example, as shown in FIG.
A matrix circuit 43 for outputting U, V, W of the 008 color system, and a LIVE output circuit 44 for calculating UV color immunity on the UV chromaticity diagram from the output of this matrix circuit 43; The gate time of this gate circuit 41 can be varied by a selection switch 46 via the gate control circuit 45.

The gate circuit 41 includes the first. Second. Third memory 29a
, 29b, 29c for opening and closing the gate. Second. It consists of third gates 418.41b and 41G, and the integrating circuit 42 also includes first, second, and third gates. third integration circuit 4a,
42b and 42c, and these integrated signals are subjected to matrix conversion in a matrix circuit 43, converted into U, V, and W signals, and further displayed as UV color points in a UVT1 output circuit 44.

The switch 46 is used to select and set a preset range, small circular or square area on the monitor screen by changing the size.

Therefore, when tristimulus light is selected, the color monitor 5
At the top, as shown on the monitor 5 in FIG. The color hemp point A is displayed, the angle θ of roughly 1ACN is displayed using the angle calculation means, and a judgment as to whether this angle θ corresponds to the normal case is displayed.

This processing process is shown in FIG. In other words, when the chromaticity sieve is applied to the test part, a similar measurement is performed on the normal part in advance, data stored in a storage means (not shown) is read out, and the chromaticity N for the normal part is determined. The convergent white point C is read out and displayed on the color constellation to calculate 1ACN. This angle is then compared with a normal angle or an abnormal angle, and the results are output and displayed on a color monitor.

The effectiveness of the diagnostic method of displaying the chromaticity of the test area on the above-mentioned chromaticity and performing spectroscopic diagnosis by calculating the angle θ will be explained below.

- It is thought that the spectral quality changes depending on the distance to the subject within the shell, the angle of illumination, etc.

In other words, Fig. 7(a) and (b) show the spectral reflection characteristics when changing the distance and angle to the color patch, for example, the R1 color patch.
Shown below. It can be seen from this figure that when the measurement conditions are changed, the shape of the spectrum does not change, but the absolute value of the reflectance changes significantly.

Therefore, CIE-1960uv chromaticity value (observation 3 [D65)
FIG. 8 shows the results of calculations for R1 and R2 color chips. As is clear from this figure, the chromaticity values measured at different distances and angles are v = 01421u + for R1.
0.202, v= 1.527u -0 for R2 color chip
,0133. Furthermore, as shown in Figure 9, the chromaticity values measured for 35 combinations of the other 16 color chips are all on a straight line with (0,188, 0,276) as the intersection point. Interesting experimental results were obtained. Note that the standard deviation of the 18 types of color patches at this coordinate was u -0,0077, v = 0.0120r.

The chromaticity value of D65 is (0,198,0,312), and the chromaticity value of endoscope illumination (measured by a spectroradiometer) is (0,28
6°0.331), which does not match the chromaticity value of the intersection.

In other words, the coordinates of the intersection point can be considered as a basic stimulus including the optical system, illumination system, etc. of this endoscope spectrometer.

Therefore, by using the dominant wavelength based on this basic stimulus, it is possible to eliminate the effects of distance and illumination angle.

In other words, regardless of the measurement distance and angle, the dominant wavelength remains the same, and the extensions of each chromaticity point toward the center of the chromaticity diagram intersect at one point.

Furthermore, the extension of each chromaticity point toward the center of the chromaticity diagram converges on a point that depends on the optical characteristics of the endoscope system and the measurement system, that is, a point that is considered to be the basic stimulus. The point extending in the opposite direction and intersecting the spectral locus is considered to be the dominant wavelength for the previous basic stimulus.

The following is predicted from the above measurement results.

In other words, if there is some kind of hue or color difference between the normal part and the Tatsunoki part, it is predicted that the dominant wavelength of the normal part will deviate from the dominant wavelength on the chromaticity diagram. A diagnostic method can be considered that uses the deviation as a standard to determine whether the area is normal or not.

In this case, the dominant wavelength of the normal part will depend on the spectral characteristics of the endoscope used for measurement, but even in that case, the normal part will only move on the dominant wavelength line on the chromaticity diagram. It can be said that a diagnostic method that determines whether or not the area is normal based on the degree of deviation from the dominant wavelength of the normal area as a reference has objectivity even when using different measurement systems.

Based on this idea, normal areas and various abnormal areas are displayed and classified on a chromaticity diagram as shown in FIGS. 10 and 11.

FIG. 10 shows the distribution of data specifically measuring the color characteristics of a single patient's gastric mucosa measured using an endoscope (OMA). Moreover, FIG. 11 shows the distribution situation for a plurality of patients who were similarly measured. It can be seen that each of them shows a certain special tendency.

According to this first embodiment, the chromaticity points of the normal area and the examined area are calculated, and the angle between these chromaticity points and the focused white point is compared with predetermined angle data to detect the lesion. It can provide useful auxiliary information for diagnosis in real time.

In addition, in the first embodiment, since illumination is performed using tristimulus values, the tristimulus value X is determined from the output of the integrating circuit 42.
, Y, Z are directly generated, and by matrix transformation, UV
Since the chromaticity points (U, V) on the chromaticity diagram can be determined, the UV chromaticity point N of the test area can be determined with high accuracy. Furthermore, x
When displaying on the y chromaticity diagram, the output of the integrating circuit 42 is converted to the xylii output circuit, that is, x=X/ (X+Y+Z),
The chromaticity point (x, y
) may be displayed. In this case, it goes without saying that the chromaticity point and focused white point of the normal area are also displayed with the same xy chromaticity on top.

Further, even when a color image of the tristimulus light is input to a spectroscopic measurement means to measure chromaticity, the correction factor is small and highly accurate spectroscopic measurement can be performed.

FIG. 12 shows a second embodiment of the invention.

In this embodiment, the electronic scope 51 is of a color filter built-in type using a CCD 53 having a color filter array 52. Further, the light source unit 54 condenses white light generated by a lamp 55 with a lens 56 and irradiates it onto the incident end surface of the light guide 57.

The object illuminated with white light is focused on the imaging surface of the CCD 53 by an objective lens 58 via a half mirror 59. At that time, G and Gy shown in FIG.

The colors are separated by a Ye three-color filter array 52.

The CCD 53 is read by applying a drive signal from the driver 6o, and after being amplified by the amplifier 62 in the video processor 61, the CCD 53 is read out by the application of a drive signal from the driver 6o.
will be passed through. The above LPF63°64 is, for example, 3M1l
z It shows a cutoff characteristic of 10.8MHz, and the signals passed through these are divided into a luminance signal YH in the ^ range and a luminance signal YL in the low range, and are sent to the process circuit 66.
．． 67, and γ correction and the like are performed. ff1r on the high frequency side through the process circuit 66! 1 signal Y
H is input to the color encoder 69 after being subjected to horizontal contour correction, horizontal aberration correction, etc. in the horizontal correction circuit 68. Further, the low-frequency side luminance signal YL passed through the process circuit 67 is input to a matrix circuit 71 for displaying an image, and is also input to a correction circuit 73, where tracking correction is performed.

On the other hand, BPF65 with a passband of 3.58±0.5MH2
A color signal component is extracted by passing through the color signal, and this color signal component is input to an IHDL (11-1 delay line) 74, an adder 75, and a subtracter 76, and color signal components B and R are separated and extracted. In this case, 1) the output of the IDL 74 is processed by the process circuit 67, and further processed by the vertical correction circuit 7.
The low frequency side luminance signal Y after vertical aperture correction in step 7 is
The mixer 78 mixes the mixture, and the mixed output is sent to the adder 75.
and is input to the subtracter 76. Thus, the color signal B of the adder 75 and the color signal R of the subtractor 76 are input to the γ correction circuits 81 and 82, respectively, and are γ corrected using the lower frequency side luminance signal YL passed through the correction circuit 73. , respectively demodulator 8
3.84, and after being converted into demodulated color signals B and R, the signals are input to the matrix circuit 71. The matrix circuit 71 generates color difference signals R-Y, B-Y, which are then input to the color encoder 69, which generates a luminance signal obtained by mixing the luminance signals YL and YH, and color difference signals R-Y, B-Y.
is mixed with a chroma signal which is orthogonally demodulated using subcarriers, and further superimposed with a synchronization signal, and a composite video signal is output from the NTSC output terminal 85.

By the way, a part of the light is reflected by the half mirror 59 and received by the light receiving element 86 for chromaticity measurement.

The photoelectric conversion signal output of this light receiving element 86 is transmitted to the color meter 8.
7, the chromaticity is measured, and the chromaticity signal is input to the angle calculation unit 88, which calculates the chromaticity between the specified points, that is, the chromaticity of the normal part and the focused white point C as in the first embodiment. The angle between the connecting straight line and the straight line connecting this point C and the chromaticity point N of the subject detected by the jJ plater 87 is calculated, and this calculated angle is used in the superimpose circuit 8.
9, the signal is superimposed on the video signal and output, and displayed on a TV monitor.

The color meter 87 is connected to a measurement point designation circuit 9.
1, it is possible to specify the measurement range or measurement point, and the color meter 87 is used for the specified range.
outputs its chromaticity.

Note that a synchronizing signal is inputted to the driver 60 by a synchronizing signal generating circuit 92, and a drive signal synchronized with this synchronizing signal is output. Further, this synchronizing signal generating circuit 92 is input to a pulse generator 93 and outputs various timing pulses.

According to this second embodiment, in addition to normal color video display, the chromaticity of a desired region can be displayed on the same monitor.

Although this second embodiment uses an electronic scope 51 with a built-in color filter 52, it is also applicable to a type of electronic scope 51 that does not have a built-in color filter 52 and performs field-sequential illumination.

In addition, in the above-mentioned FIG. 12, the entire surface half mirror 59 is reflected by the slope area, but as shown in FIG. Part) It may be a prism 97 that reflects the light and transmits all the light in the transmitting part 96 outside of the prism 97.

FIG. 15 shows the main parts of a third embodiment of the present invention.

In this embodiment, an electronic scope 102 using an optical fiber 101 is used instead of the light receiving element 86 in the second embodiment shown in FIG. analyzer)
87', and the chromaticity is output. The rest is the same as the second embodiment.

FIG. 16 shows the main parts of a fourth embodiment of the present invention.

In this embodiment, for example, in the second embodiment, the half mirror 59 and the light receiving element 86 are not provided at the tip of the electronic scope, and instead, a part of the light guide 57 is used for spectroscopic measurements.

That is, by branching the light source side end of some of the fibers 57' of the light guide 57 and guiding them to the spectrometer (spectroscopy means) 105, the light incident on the end face of the light guide 57' is spectrally divided. The device 105 determines chromaticity and performs spectral diagnosis.

FIG. 17 shows the main parts of a fifth embodiment of the present invention.

In this embodiment, a half mirror is used in the second embodiment.
59, channel 112 of electronic scope 111 is not provided with chromaticity measurement means such as light receiving element 86 in electronic scope
A probe 113 for chromaticity measurement is passed through the inside. The light received by the probe 113 is input to an optical spectrum analyzer 114, where the chromaticity is calculated and spectroscopic diagnosis can be performed.

FIG. 18 shows a modification of the probe shown in FIG. 17.

In this embodiment, the chromaticity measurement probe 113 includes an illumination light guide 122 connected to a light source 121 as shown in FIG. 18, and a fiber 122a forming this light guide 122 as shown in FIG. ,...,
An optical fiber 123 in the center of 122a is used for chromaticity measurement, and the light received by this optical fiber 123 is guided to an optical spectrum riser 124 to measure chromaticity and perform spectroscopic diagnosis.

FIG. 20 shows the main part of a sixth embodiment of the present invention.

In this embodiment, for example, in the second embodiment, CC
A fiberscope 132 using an image guide 131 is used in place of the D53 to enable chromaticity measurement and spectroscopic diagnosis.

In addition, in the second embodiment shown in FIG.
59 and the light receiving element 86 are not provided in the electronic scope 51, and instead of the color filter 52 shown in FIG. 13, a color filter section 141 used for general video display as shown in FIG. A filter section 142 and a filter section 143 may be used to separate the plan book when it is read out. Further, as shown in FIG. 22, instead of installing a filter in the center, a color filter 145 may be provided in which a colorimetric element 144 is provided in this part. Also, in FIG. 12, x and y are used instead of the lamp 55.

It is also possible to illuminate with a lamp having a spectral distribution of light with tristimulus values of 2, and accordingly, the matrix circuit 71 may also display the tristimulus values.

[Effects of the Invention] As described above, according to the present invention, in addition to the normal signal processing means for displaying in color, there is also a color directivity measuring means for the test area, and a method for determining whether the test area is normal based on the chromaticity. Since a spectroscopic judgment means is provided, in addition to normal endoscopy, spectroscopic diagnosis can be performed, and a more appropriate diagnosis can be made.

[Brief explanation of the drawing]

1 to 11 relate to a first embodiment of the present invention, FIG. 1 is a block diagram of the first embodiment, FIG. 2 is a front view of a rotating filter, and FIG. 3 shows spectral tristimulus values. Spectrum diagram, Figure 4 is an explanatory diagram of the operation of the first embodiment, Figure 5 is a configuration diagram of a circuit such as a chromaticity meter, explanatory diagram showing the sixth thing, and Figure 10 is a measurement result of the normal part and abnormal part. on a chromaticity diagram, Fig. 11 is a diagram in which more measured data than Fig. 10 is plotted on a chromaticity diagram, Fig. 12 is a configuration diagram of the second embodiment of the present invention, and Fig. 13 14 is a front view showing a color filter array, FIG. 14 is an explanatory diagram showing a modification of the half mirror in the second embodiment, FIG. 15 is a configuration diagram showing the main parts of the third embodiment of the present invention, and FIG. 16 18 is an explanatory diagram showing a modified example of the probe in the fifth embodiment, and FIG. 19 is an enlarged view of the tip surface of the probe in FIG. 18. A front view, FIG. 20 is a configuration diagram showing the main parts of the sixth embodiment of the present invention, FIG. 21 is an explanatory diagram showing a modification of the color filter in the second embodiment of the present invention, and FIG. 22 is a diagram showing the modification of the color filter in the second embodiment of the present invention. It is an explanatory view showing still another modification of a color filter in a 2nd example. 1... Diagnostic mirror spectroscopic diagnostic equipment 2... Electronic scope 3... Light source device 4...
Signal processing device 5... Color monitor 12... Rotating filter 14, 14.14z... Tristimulus value filter 22...
・C0D 33...Superimpose circuit 34...Chromaticity meter circuit Fig. 5 Fig. 7 μ Wavelength (nm) Chi- Wavelength (nm) Fig. 8 0 0, + 0.2 0.3
0.4 0.5. 0.6u(J
(J 1st
Figure 4 Figure 17 Old figure Proceedings Masade Ichi (spontaneous) Commissioner of the Patent Office Kunio Ogawa 1, Indication of the case Patent application No. 260018 of 1988
No. 2, Title of the invention Transendoscopic spectroscopic diagnosis IA No. 3, Relationship with the case of the person making the amendment Patent applicant representative Satoshi Shimoyama Department 5. Date of amendment order (self-initiated) 6. Subject of amendment Akira ms r4a, 42b in column 1 of "Detailed Description of the Invention", page 12, line 5 of Mei Ill.
. ``From 42c'' is corrected to ``From r42a, 42b, 42C.'' 2. Delete the statement "The shape of the spectrum does not change, but" on page 13, line 18 of the specification.

Claims (1)

[Claims] An endoscope apparatus comprising an illumination means for illuminating a subject, a signal processing means for receiving reflected light from the subject and processing the signal to generate a video signal, and a monitor means for displaying a color display based on the video signal, A transendoscopic spectroscopic diagnostic apparatus comprising: a chromaticity measuring means for at least a part of a subject; and a means for displaying the chromaticity of the measurement site based on the output of the chromaticity measuring means.