JPH01101963A - Endoscopic spectral diagnostic apparatus - Google Patents

Abstract

PURPOSE:To obtain highly accurate data effective for the diagnosis of a lesion part in real time, by increasing the intensity of the emitted light from a light source by the recording start indication of a static picture to perform the recording and spectral measurement of the static image. CONSTITUTION:When the release button 74 of a camera 71 is pressed, a light source lamp 31 emits stroboscopic light and the photograph of a region to be measured is taken by the camera 71. The release signal from the synchronous contact 75 of the camera 71 is inputted to a trigger unit 80 and a trigger pulse delayed by a predetermined time is given to a signal processing part 55. By this constitution, the signal processing part 55 starts spectral measurement in synchronous relation to the stroboscopic emission of light from the light source lamp 31 and the taking of the photograph of the region to be measured by the camera 71.

Description

[Detailed Description of the Invention] [Industrial Application Field] The present invention relates to a spectroscopic diagnostic device using an endoscope, and particularly to a transendoscopic spectroscopic diagnostic device capable of recording still images of a spectroscopic measurement site. Related to.

[Problems to be solved by conventional techniques and inventions] In recent years,
By inserting the Ill-length insertion section into the body cavity, the endoscope can be used to observe the intra-body cavity fissures, etc., and perform various therapeutic procedures as necessary using the treatment instrument inserted into the treatment instrument channel. came to be used.

Incidentally, 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, JP-A-61-10
In Japanese Patent No. 7482, white light is guided to a desired position,
A semi-transparent mirror that transmits reflected light from an illuminated object; a universal filter that transmits only a desired wavelength band of the reflected light; and multiple types of images using multiple types of wavelength light output from the universal filter. An optical imaging device has been proposed that includes means for measuring the intensity of each part of the image as an image, and means for obtaining the intensity difference between corresponding parts of the plurality of types of images. In this method, a plurality of images obtained from a universal filter are superimposed 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
Japanese Patent Publication No. 79251 proposes an image observation and diagnosis apparatus that includes a light branching mirror at the tip of an endoscope, performs spectroscopic measurements of areas that cannot be viewed directly, processes the spectra, and performs spectroscopic analysis of objects.

By the way, the above-mentioned Japanese Patent Application Laid-Open No. 61-107482 states that a universal filter is used to selectively extract the spectral difference between a normal area and an abnormal area, and multiple images are superimposed to enlarge the intensity difference. There is no presentation of specific wavelength characteristics, and it is stated that selective wavelength images are superimposed and displayed by computer processing, but it is not possible to specifically state this content. In addition, this publication discloses an example in which images using selective wavelengths are compared to film, but in the field of medical diagnosis,
To obtain a magnified intensity difference image, it is necessary to determine whether it is better to use a combination of positive and negative film or a combination of negative and positive when recording the image in the desired y-scene area for the universal filter to be used. Deciding on this is extremely troublesome for doctors whose primary purpose is diagnosis. Furthermore, under light conditions that cannot be said to be sufficient even for normal endoscopy, if a universal filter that only passes the desired wavelength range is used, and even a polarizing filter is used, the amount of light is extremely small. 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 time. Further, although the method disclosed in Japanese Patent Application Laid-Open No. 60-79251 states that spectroscopic analysis of a subject is performed by calculating spectra, there is no specific disclosure of providing highly accurate data in real time.

To deal with this, the applicant filed the patent application filed earlier in 1983.
No. 2-113512, the focused chromaticity point (C) determined by the spectral characteristics of an endoscope including a light source determined in advance and the spectral characteristics of the subject, and the spectral characteristics of the normal part of the subject obtained by a spectroscopic measurement means. The ZACN is determined from the chromaticity point (N) calculated from the chromaticity point (N) and the chromaticity point (A) calculated from the spectral characteristics of the abnormal area obtained by the spectroscopic measurement means, and this is stored in advance at the lesion cutting angle. We are proposing a transendoscopic spectroscopic diagnostic device that can diagnose a lesion by comparing the data.

By the way, when measuring the spectral characteristics of a subject and recording a still image of the subject, for example taking a photograph, using the transendoscopic spectroscopic diagnostic device, if the measurement and photography are performed separately, There is a possibility that the measurement data and the photographed region do not correspond. Further, when taking a photograph by increasing the emission intensity of a light source by emitting a strobe light or the like, it is desirable to perform measurements corresponding to the increase in emission in order to reduce noise. However, if you start measurement at the same time as sending a signal instructing strobe emission to the light source, there is a time lag between the signal instructing strobe emission and the strobe light being emitted, making it difficult to accurately measure when the strobe is emitted. Can not.

[Objective of the Invention] The present invention has been made in view of the above circumstances, and is capable of providing highly accurate data in real time that can serve as a useful aid in diagnosis of lesions, as well as increasing the light emission intensity of a light source. It is an object of the present invention to provide a transendoscopic spectroscopic diagnostic device that can synchronize spectroscopic measurement and recording of a still image of the measurement site.

[Means for Solving the Problems] The transendoscopic spectroscopic diagnostic apparatus of the present invention includes an endoscope, a spectroscopic measuring means for spectroscopically measuring return light from a subject, and a spectroscopic system of the endoscope including a light source. Determined by the characteristics and the spectral characteristics of the specimen,
ZACN is calculated from the focused chromaticity point (C) where the chromaticity points of the subject are focused, the chromaticity point of the normal part of the subject (N), and the chromaticity point of the measurement target part in the subject (A). a still image recording means for recording a still image of the subject; an instruction means for instructing the recording of the still image and the start of measurement; and a light source in synchronization with the instruction by the instruction means. control to increase the light emission intensity of the light source, and to start measurement by the spectroscopic measurement means with a predetermined time delay from the instruction in response to a time delay from the instruction until the light emission intensity of the light source actually increases. means.

[Operation 1] In the present invention, the light emission intensity of the light source is increased by the instruction to start recording a still image by the instruction means, and the still image is recorded, and the time from this instruction until the light emission intensity of the light source actually increases is increased. Corresponding to the time delay, spectroscopic measurement is started after a predetermined time delay from the instruction.

[Example] Hereinafter, the present invention will be described in detail with reference to the drawings.

Figures 1 to 6 relate to the first embodiment of the present invention.
The figure shows the general configuration of a transendoscopic spectroscopic diagnostic device.
Figure 2 is an explanatory diagram showing the surroundings of the camera, Figure 3 is a block diagram showing the configuration of the trigger unit, Figure 4 is a waveform diagram to explain the operation of this embodiment, and Figure 5 is an explanation of color characteristics. FIG. 6 is a block diagram of a derivation comparator.

As shown in FIG. 1, a transendoscope spectroscopic diagnostic apparatus 1 includes an endoscope (fiberscope) 2. As shown in FIG.

This endoscope 2 includes a flexible and elongated insertion section 3, a large diameter operation section 4 connected to the rear of the insertion section 3, and a light extending from the side of the operation section 4. A guide cable 5 is provided. A light source connector 6 is provided at the end of the light guide cable 5 and is detachably connected to the light source device 3o. Furthermore, an eyepiece section 7 is provided at the rear of the operation section 4 .

An objective lens 9 is provided at the distal end 8 of the insertion section 3, and an eyepiece 10 is provided at the eyepiece section 7. An image guide 11 that connects the objective lens 9 and the eyepiece 10 is inserted inside the insertion section 3 and the operation section 4. Furthermore, a first light guide 12 is inserted into the insertion section 3 and transmits illumination light for illuminating the observation site from the distal end section 8, and this first light guide 12 is connected to the operating section 4 and the light guide It is inserted into the cable 5 and connected to the light source connector 6, and is connected to the optical IQ device 30 by the light source connector 6, and the light source device 30 is connected to the light source connector 6.
Illumination light emitted from a light source lamp 31 provided inside can be transmitted. The light source bag @30 includes a light source control circuit 32 that controls the amount of light emitted from the light source lamp 31, and is capable of strobe light emission.

On the other hand, an observation adapter 21 provided at the tip of a light guide scope 20 is detachably attached to the eyepiece 7 of the endoscope. This observation adapter 21 includes an observation lens 22 for observing an optical image obtained through the eyepiece 7.
is provided.

Furthermore, a splitting prism 23 is provided on the optical axis of the observation lens 22 on the eyepiece 10 side, and the splitting prism 23 splits the optical image.

That is, this dividing prism 23 divides the light amount of the optical image from the endoscope 2 side, and sends a part of it to the observation lens 22.
The remainder is transmitted 16' to the light guiding scope 20.

The light guide scope 20 is connected to a second light guide scope within a flexible cable 24.
A light guide 25 is inserted through the light guide scope 20, and an imaging lens 26 is disposed on one end side of the light guiding scope 20, that is, on the incident end surface of the second light guide 25. The optical image divided by the dividing prism 23 is input to the second light guide 25 by
It is designed so that it can be incident on the JJ end face. Further, a measurement adapter 27 is provided on the other end side so that it can be detachably connected to the spectrometer 40. and,
By connecting this measurement adapter 27 to the spectrometer 40, the other end of the second light guide 25 is connected to the spectroscopic means of the spectrometer 40.

The spectrometer 40 is provided with a spectroscopic means consisting of a plurality of reflection mirrors 41... and a spectroscopic diffraction grating 42, and is capable of spectrally dispersing the optical image incident on the light guiding scope 20'. There is. Furthermore, this separated light is sent to a detector 4 consisting of a multi-channel photosensor.
3.

On the other hand, a mask 51 is provided in the eyepiece section 7 at a portion facing the output end surface of the image guide 11.
This mask 51 is attached with a circular reticle that is displayed within this observation field. The optical axis of the second light guide 25 coincides with the optical axis of the reticle, has the same size as the image of the reticle, and blocks light outside the reticle.

The output end 52 of the second light guide 25 is formed by arranging optical fibers in a flat shape, for example, in a negative row, and is formed into a flat plate shape. This output end portion 52 is provided within the measurement adapter 27. A slit member 53 is installed in the main body portion of the spectrometer 40 facing the flat output end 52 to pass the light emitted from each of the optical fibers arranged in the flat plate.

On the other hand, in the detector 43 consisting of the full one-channel photo sensor, each detection pixel portion is formed vertically long. The above-mentioned output end 52 is connected to the spectrometer 40.
When mounted on the detector 43, it is located at a position optically conjugate to the light receiving surface of the detector 43. That is, the detector 43
The position corresponds to the position lined up on both of the IH yarns in the center of the line.

The signal detected by this detector 43 is transmitted to the signal processing unit 5
5, where processing such as A/D conversion, wavelength calibration, and noise removal is performed.The output is sent to a display 56 that displays the spectral characteristics, and the spectral characteristics of the test portion 50 are displayed. It looks like this. Further, the output of the signal processing section 55 is input to an arithmetic comparator 58 via a so-called GP-IB line 57, and the result is displayed on an image display device 59.

The arithmetic comparator 58 is connected to the line 5 as shown in FIG.
7, a chromaticity calculation means 62 for calculating chromaticity from the reading means 61;
Data retrieval means 63 for retrieving chromaticity data of the focused white point
, angle calculating means 64 for calculating the angle between each chromaticity point from the chromaticity point of the focused white point, and the data calling means 6 for calculating the angle.
Angle comparison means 65 for comparing with the lesion-specific angle obtained from 3.
, the image display device 59 uses the results as image display data.
and an output means 66 for outputting to.

The data obtained by this arithmetic comparator 58 is displayed on an image display device 59. The data calling means 63 may be provided anywhere before the angle calculating means 64.

Further, a camera 71 can be attached to the observation adapter 21 via an adapter 70 so that an image of the subject 50 can be recorded.

The camera 71 includes a camera body 7, as shown in FIG.
2, and a release signal auxiliary output section 73 attached to the camera body 72. The camera body 72 includes a release button 74 and a synchronization contact 75 that outputs a release signal that instructs the light source device 30 to emit strobe light in synchronization with the opening and closing of the shutter operated by pressing the release button 74. We are prepared. This synchro contact 75 is connected to the light source control circuit 32 of the light source device 30 via a synchro cord 79.

This light source control circuit 32 includes the synchro contact 7
When the release signal from 5 is input, the light source lamp 3
1 is designed to emit strobe light. Further, the release signal auxiliary output section 73 includes an auxiliary release button 7
6 and the suppression operation of this auxiliary release button 76,
A release signal output terminal 77 that outputs a release signal is provided. Note that the auxiliary release button 76 is not linked to the shutter of the camera body 72, and photographing is not performed even if the auxiliary release button 76 is pressed. Further, the synchronization contact 75 and the release signal output terminal 77 are electrically connected by a signal line 78.

The release signal output from the release signal output terminal 77 is input to the signal processing section 55 via the trigger unit 80. Further, the release signal from the synchronization contact 75 is also outputted from the release signal output terminal 77 via a signal line 78. As shown in FIG. 3, the trigger unit 80 includes a measurement interval maintenance circuit 81 and a delay circuit 82.
, a trigger pulse width setting circuit 83 that sets the trigger pulse width to the signal processing section 55 , and a drive circuit 84 that sends the trigger pulse to the signal processing section 55 . Further, the delay amount of the delay circuit 82 can be adjusted by a coarse adjustment knob 86 and a fine adjustment knob 87 as shown in FIG. Then, the signal processing section 55
is adapted to input a trigger pulse from the trigger unit 80 and start signal processing.

Next, with reference to FIGS. 4 and 5, the operation of the spectroscopic laboratory apparatus 1 of this embodiment will be explained.

First, the insertion section 3 of the endoscope 2 is introduced into the body cavity, and the subject 50 is observed through the observation adapter 21 of the light guiding scope 2o. Then, change the position of the tip 8 of the insertion section 3 and place the object 50 to be measured on the reticle displayed within the observation field.
The image of is inscribed.

On the other hand, at this time, the image of the subject 50 is physically observed through the observation adapter 21, and part of the light is split by the splitting prism 23 and passed through the second light guide 25 of the light guide scope 20. transmitted. The incident end face of the second light guide 25 is located at a position conjugate to the reticle and has the same size as the image of the reticle on the second light guide 25. The only light emitted is the light emitted from the test section 50.

This light is separated into a necessary wavelength range by the spectrometer 40 and enters the light receiving surface of the detector 43 . At this time, the spectrally separated wavelength range expands in the arrangement direction of each pixel section of the detector 43, and each wavelength component is measured in each pixel section.

This measured data is processed by the signal processing section 55 and displayed on the display device 56. Furthermore, if the signal processing section 55 stores data on a normal region and data on a diseased region in advance, the diagnosis of the subject 50 can be performed by comparing the data.

On the other hand, the measurement data of the normal part performed prior to the measurement of this test part 50 is read by the signal processing part 55 by the spectral data reading means 61 of the arithmetic comparator 58, and
The chromaticity point (N) of the normal area is calculated. Next, the measurement data of the test portion 50 is also read by the spectral data reading means 61 from the signal processing section 55, and the chromaticity point (A) thereof is calculated by the chromaticity calculating means 62. On the other hand, the chromaticity point data of the focused white point (C) recorded in advance is retrieved from the data calling means 6.
Called by 3. In addition, the focused white point (C) is
It is determined by the spectral characteristics of the endoscope including the light source and the spectral characteristics of the subject, and is the point at which the chromaticity points of the subject are focused. next,
As shown in FIG. 5, the angle calculating means 64 calculates, for example, IAcN (-α) on the UV chromaticity diagram, and this is compared with the predetermined angle data previously called by the data calling means 63. The result is outputted by the output means 66 and displayed by the image display device @59. For example, if it is α-5 degrees, it can be determined whether it is normal or abnormal. This alerts the physician to take a closer look at the area.

Note that if the angle α is determined to be abnormal, for example,
The image display device 59 may be used to issue the υ notification.

If data specific to cancer, ulcer, erosion, etc. is inputted as the predetermined angle data, diagnosis can be made by comparing these data with the angle data of the test area.

In this embodiment, an image of the object to be inspected 50 can be recorded by a camera 71 attached to the observation adapter 21 via an adapter 70.

As shown in FIG. 4(a), when the release button 74 of the camera body 72 is pressed, the shutter (not shown) of the camera body 72 opens and closes, and a photograph is taken as shown in FIG. 4(b). In addition, in synchronization with this, a release signal instructing strobe light emission is output from the synchro contact 75, and the light source control circuit 32 of the light source device 30 inputs this release signal and operates as shown in FIG. 4(C). , the light source lamp 31 emits strobe light. In this case, as shown in FIG. There is a time lag.The release signal from the synchro contact 75 is output from the release signal output terminal 77 via the signal line 78, and is sent to the trigger unit 8.
It is input to 0. From this trigger unit 80, d
The trigger pulse, which is delayed by a predetermined delay time T from the release signal by the detour path 82 and set to a predetermined width by the trigger pulse width setting circuit 83, is sent to the drive circuit 84.
This trigger pulse is outputted via the signal processing section 5.
5 is input. Then, the signal processing section 55
As shown in FIG. 1, a trigger pulse from the trigger unit 80 is input, signal processing is started, and spectroscopic measurement is performed. The coarse adjustment knob 86 is adjusted so that the delay time T in the trigger unit 80 is approximately the same as the time lag t until the light source lamp 31 actually emits strobe light in response to the release signal from the synchro contact 75.
and is set by the fine adjustment knob 87. In addition, since the time lag t differs depending on the light source, for each light source,
It is adjusted according to the time lag t. in this way,
When the release button 74 is pressed, strobe light emission from the light source lamp 31, spectroscopic measurement by the spectrometer 40 and signal processing unit 55, and photographing of the measurement site are performed in synchronization.

On the other hand, when the auxiliary release button 76 of the auxiliary release signal output section 73 is pressed, a release signal is output from the release signal output terminal 77, although photographing is not performed. As described above, this release signal is input to the signal processing section 55 via the trigger unit 80, and
The signal is output from the synchro contact 75 via the i-line 78 and input to the light source control circuit 32 of the light source 1430 via the synchro cord 79. Therefore, in this case, only spectroscopic measurements are performed in synchronization with the strobe light emission of the light source lamp 31.

As described above, according to this embodiment, by suppressing the release button 74 of the camera 71, the light source lamp 3
1 strobe light emission, a spectrometer 40 and a signal processing unit 5
The spectroscopic measurement by 5 and the photographing of the measurement site by camera 71 can be performed synchronously. Moreover, the signal processing by the signal processing unit 55 is started after a delay time T, which is set to be approximately the same as the time lag t until the light source lamp 31 actually emits strobe light due to the release signal from the synchronizing contact 75. Therefore, it is possible to accurately perform measurements during strobe light emission, the measurement site and the imaging site match, and it is possible to obtain highly accurate data with less noise.

Alternatively, only measurement can be performed by pressing the auxiliary release button 76 of the auxiliary release signal output section 73. Therefore, for example, normally only the measurement is performed using the auxiliary release button 76, and the release button 74 of the camera body 72 is pressed as necessary depending on the waveform on the display 56 or the alarm issued by the image display device 41. , it is also possible to perform photography and measurement at the same time.

Note that in this embodiment, the release signal auxiliary output section 73 may not be provided, and photographing and measurement may always be performed.

FIG. 7 is an explanatory diagram showing the surroundings of a camera in a second embodiment of the present invention.

In this embodiment, the release signal output terminal 77 of the camera 71
The light source device 30 and the signal processing section 55 are connected via the trigger unit 90.

The trigger unit 90 outputs a trigger pulse with a delay time T to the signal processing section 55 through the circuit shown in FIG.
outputs an undelayed release signal.

The other functions and effects of Structure 2 are the same as those of the first embodiment.

FIG. 8 is an explanatory diagram showing the surroundings of a camera according to a third embodiment of the present invention.

In this embodiment, the release signal auxiliary output section 73 in the first and second embodiments is not attached to the camera body 72. A synchronization contact 75 of the camera body 72 is connected to a light source device 30 and a signal processing section 55 via a trigger unit 80 . Further, in this embodiment, a foot switch 92 is provided, and this foot switch 92 also has the following features:
The light source device 30 is connected to the signal processing section 55 via the trigger unit 80.

In this embodiment, when the release button 74 of the camera body 72 is pressed, the light source lamp 31
strobe light emission, spectrometer 40 and signal processing section 55
The spectroscopic measurement by and the photographing of the measurement site are performed synchronously. On the other hand, when the foot switch 9'2 is pressed, only spectroscopic measurement is performed in synchronization with the flash emission of the light source lamp 31.

Other functions and effects of the configuration 1 are the same as those of the first embodiment.

FIG. 9 is an explanatory diagram showing a schematic configuration of a transendoscopic spectroscopic cutting device according to a fourth embodiment of the present invention.

Transendoscope spectrometer 1 of this embodiment! The li device 100 includes a screen-sequential electronic internal view &1101 and the electronic internal view 11101.
a light source device that supplies illumination light to the electronic endoscope 101;
an electric light source unit 120 integrated with a video processor 130 that performs signal processing for the electric light source unit 1;
20, and a still image recording device 160 connected to the video processor 130.

The electronic family celebration! 11101 is an elongated insertion portion 102;
An operating section 103 connected to the rear of the insertion section 102;
A universal cord 104 extends from the side of the operation section 103, and a connector 105 is provided at the tip of the universal cord 104 to be detachably connected to the electric light source unit 120.

An objective lens system 106 is provided at the distal end of the insertion section 102, and a solid-state image element, such as a CCD 107, is provided at the imaging position of the objective lens system 106. Signal lines 108 and 109 are connected to this CCD 107,
These signal lines 108 and 109 are inserted into the insertion portion 102 and the universal cord 104 and connected to the contacts 105a and 105b of the connector 105. Further, inside the insertion section 102, the distal end surface is located inside the insertion section 102.
A light guide 110 disposed at the distal end of the connector 1 is inserted, and the proximal end of the light guide 110 is inserted into the universal cord 104 and connected to the connector 1.
It is connected to 05.

Further, the operation unit 103 is provided with a freeze button 111 for instructing still image recording and measurement, and a measurement button 112 for instructing only measurement. The button 11
Signal lines 113 and 114 are connected to the terminals 1 and 112, respectively, and the signal lines 113 and 114 are inserted into the universal cord 104 and connected to the contacts 105c and 105d of the connector 105.

On the other hand, inside the electric light source unit 120, a light source lamp 1 is provided.
21 is provided between the light source lamp 121 and the incident end face of the light guide 110, and red (R), green (G), blue (
A rotary filter 123 that is rotationally driven by a motor 122 is provided on the right side of the color transmission filter for the three primary colors in B). The rotation of this rotary filter 123 is controlled by a motor driver 124 to which a synchronization signal from a timing generator 131 in the video processor 130 is input. Further, the light source lamp 1
21 is a control circuit 13 in the video processor 130;
2, the light fade is controlled.

Further, the video processor 130 in the electric light source unit 120 includes a driver 133 connected to the contact 105a of the connector 105, and the CGD 107 is activated by a driving pulse output from the driver 133 and applied via the signal line 108. It is designed to be driven.

The signal read from this COD 107 is the signal line 10
9, the signal is input to an amplifier 135 in the video processor 130, which is connected to the connector 105b. The signal amplified by the amplifier 135 is A
The signal is converted into a digital signal by the /D converter 136, and written into each of the R, G, and B frame memories 137. This R, G, B frame memory 1
37 are simultaneously read out and converted into analog signals by a D/A converter 138, a sample-and-hold circuit 139 adds, for example, a circular reticle contour signal, and the signals are sent to an NTSC encoder 140.
It is now entered into The video signal output from the NTSG encoder 140 is input into the chromaticity calculation device 150, and is also input into the still image recording device 16.
It is set to be input as 0. The still image recording device 160 is, for example, a CRT monitor, a still camera that photographs the screen of this monitor, or a magnetic disk recording device.

It consists of a floppy disk recording device, a video tape recorder, etc.

Note that the timing generator 131 receives drive pulses from the driver 133 and outputs the rotation filter 12.
The motor driver 124 is controlled so that the 30 rotations and the reading of the CGD 107 are synchronized. In addition to controlling the light amount of the lamp 121, the control circuit 132 also controls the driver 133. Amplifier 135. It controls the timing of the frame memory 137 and the D/A converter 138, and also controls whether or not the still image recording device 160 performs recording.

Further, the control circuit 132 controls the frame
By stopping writing to the screen 137, the image can be made still (frozen).

Further, a release controller 170 is provided in the electric light source unit 120, and a release signal outputted from the release controller 170 is input to the control circuit 132, and this control circuit 132 receives the release signal input. At times, the light source lamp 121 emits strobe light, the writing to the frame memory 137 is stopped, the image is frozen, and the still image recording device 1
60 to record still images.

A freeze instruction signal from the freeze button 111'bX etc. is input to the release controller 170 via the contact 105C of the connector 105 of the electronic endoscope 101, and the release controller 170, when inputting the freeze instruction signal, The release signal is output.

Furthermore, a trigger unit 171 having the same configuration as the trigger unit 80 in the first embodiment is provided in the electric light source unit 120.

The trigger unit 171 is configured to receive a freeze instruction signal from the freeze button 111 via the contact 105C and a measurement instruction signal from the measurement button 112 via the contact 105d. After a predetermined delay time from the freeze instruction signal or the measurement instruction signal, the trigger pulse output from the trigger unit 171 is input to the chromaticity calculation circuit 151 of the chromaticity calculation device 150, and this chromaticity calculation circuit 151 starts calculation when the trigger pulse is input.

Further, the measurement instruction signal from the measurement button 112 input via the contact 105d is also input to the control circuit 132, and this control circuit 132 causes the light source lamp 121 to emit strobe light when the measurement instruction signal is input. It has become.

The chromaticity calculation circuit 151 of the chromaticity calculation device 150 receives the video signal from the NTSC encoder 140 of the video processor 130, and calculates the chromaticity of the object part within the reticle from this video signal. ing. The chromaticity calculation circuit of this chromaticity calculation circuit 151 is input to the still image recording device 160 via the superimposition circuit 152, and can be displayed on the monitor of this still image recording device 160 by superimposing. ing.

Further, the superimpose circuit 152 is configured to switch whether or not to perform superimposition by a display switching circuit 153.

The chromaticity calculation circuit 151 demodulates the video signal from the video processor 130 into R, G, and B color signals, integrates the R, G, and B color signals within the reticle, and calculates a matrix from this integrated value. The circuit calculates, for example, chromaticity coordinates on a UV chromaticity diagram. Similarly to the first embodiment, /AcN (=
α) is calculated, compared with predetermined angle data, and the result is sent to the superimpose circuit 152.

Further, in this embodiment, when the calculation result of the chromaticity calculation circuit 151 is determined to be abnormal, this chromaticity calculation circuit 1
51 outputs a release instruction signal to the release controller 170. When the release instruction signal is input, the release controller 170 outputs a release signal to the control circuit 132;
As a result, the light source lamp 121 emits strobe light, and a still image is recorded.

In this example, electronic endoscopy! [The insertion section 102 of 101 is introduced into the body cavity, and the subject part is observed on the monitor of the still image recording device @160. Then, the position of the tip of the insertion section 102 is changed so that the image of the object to be measured is inscribed on the reticle displayed within the observation field of view.

When measuring and recording a still image, the freeze button 111 of the operation unit 103 is pressed. A freeze instruction signal from the freeze button 111 is input to the release controller 170 and the trigger unit 171. Then, the release controller 170 outputs a release signal to the control circuit 132, which causes the light source lamp 121 to emit strobe light, stops writing to the frame memory 137, and freezes the image. Still image recording device 160
A still image is recorded. Further, the trigger unit 17
The trigger pulse output from 1 is the colorimeter n device 15
0 is input to the chromaticity calculation circuit 151, and this chromaticity calculation circuit 151 starts calculation, while if only measurement is to be performed, the measurement button 112 of the operation section 103 is pressed. This measurement button 112
The measurement instruction signal from is input to the control circuit 132 and the trigger unit 171.

Then, the control circuit 132 controls the light source lamp 12.
1 is emitted with a strobe, and a trigger pulse outputted from the trigger unit 171 after a predetermined delay time from the measurement instruction signal is input to the chromaticity calculation circuit 151 of the chromaticity calculation device 150, and this chromaticity calculation circuit 151
starts calculation.

Further, if the calculation result of the chromaticity calculation circuit 151 is determined to be abnormal, a release instruction signal is output from the chromaticity calculation circuit 151 to the release control 0-5170, and the release controller 170 circuit 13
2, and as a result, the light source lamp 12
1 is flashed and a still image is recorded.

In this way, according to this embodiment, similarly to the first embodiment,
By pressing the freeze button 111 of the electronic endoscope 101, the light source lamp 121 emits strobe light,
Measurement by chromaticity calculation circuit 151 and still image recording device 16
Recording of a still image of the measurement site by Mυ can be performed in accurate synchronization with Mυ shadow.

Furthermore, in this embodiment, when only measurement is performed, if the calculation result of the chromaticity calculation circuit 151 is determined to be abnormal, a still image of the abnormal area can be automatically recorded. can.

It should be noted that the present invention is not limited to the above-mentioned embodiments; for example, in addition to an instruction means for instructing the start of still image recording and measurement, and an instruction means for instructing the start of only measurement, it is also possible to use an instruction means for instructing the start of recording only still images. An instruction means for giving instructions may be provided.

In addition, the observation means may be a fiberscope with a field-sequential or simultaneous TV camera attached to the eyepiece, and in the case of an electronic scope, the color image transport method is limited to the field-sequential method. It may be a simultaneous type.

[Effects of the Invention] As explained above, according to the present invention, it is possible to generate highly accurate data in real time that can serve as an effective auxiliary means for diagnosing a lesion in a clinical setting without imposing a burden on both the patient and the doctor. In addition to increasing the emission intensity of the light source,
This has the advantage of being able to synchronize the spectroscopic measurement with the recording of a still image of the measurement site.

[Brief explanation of the drawing]

Figures 1 to 6 relate to the first embodiment of the present invention.
The figure is an explanatory diagram showing the general configuration of a transendoscopic spectroscopic diagnostic device,
Figure 2 is an explanatory diagram showing the surroundings of the camera, Figure 3 is a block diagram showing the configuration of the trigger unit, Figure 4 is a waveform diagram to explain the operation of this embodiment, and Figure 5 is an explanation of color characteristics. 6 is a configuration diagram of the performance comparison means, FIG. 7 is an explanatory diagram showing the surroundings of the camera in the second embodiment of the present invention, and FIG. 8 is a diagram showing the surroundings of the camera in the third embodiment of the present invention. 1 and 9 are explanatory diagrams showing a schematic configuration of a transendoscopic spectroscopic diagnostic apparatus according to a fourth embodiment of the present invention. 1... Transendoscope spectroscopic diagnostic device 2... Endoscope 3... Insertion section 30...
Light source device 31...Light source lamp 32...Light source control circuit 40...Spectrometer 55...Signal processing unit 71...Camera 74...Release button 75...Synchro contact 76... Auxiliary release button 77...Release signal output terminal 80...Trigger unit agent Patent attorney Susumu Ito 71.1゛wo°
. Figure 2 Figure 3 Figure 5 Copper Figure 7

Claims (1)

[Claims] An endoscope equipped with an illumination means for irradiating a subject with light from a light source capable of increasing emission intensity and an observation means for observing the subject by receiving return light from the subject; The convergence chromaticity point (C), where the chromaticity points of the subject are focused, is determined by the spectroscopic measurement means that spectrally measures light, the spectral characteristics of the endoscope including the light source, and the spectral properties of the subject, and the normality of the subject. a calculation means for calculating ∠ACN from the chromaticity point (N) of the area and the chromaticity point (A) of the measurement target part in the subject; and a still image for recording a still image of the subject observed by the observation means. an image recording means; an instruction means for instructing the start of recording and measurement of the still image; and increasing the emission intensity of the light source in synchronization with the instruction from the instruction means, and increasing the emission intensity of the light source based on the instruction. In response to the time delay before increasing to
A transendoscopic spectroscopic diagnostic apparatus comprising: a control means for causing the spectroscopic measuring means to start measurement after a delay of a predetermined time from the instruction.