JPH04341232A - Electronic endoscope system - Google Patents

Abstract

PURPOSE:To provide the electronic endoscope system which can display simultaneously plural images obtained from plural photographing elements on one high vision monitor without causing the deterioration of resolution. CONSTITUTION:The system is provided with an electronic endoscope 2 provided with plural CCDs 7a to 7e, a controller 3 for executing a signal processing to output signals of these CCDs 7a to 7e, and also, generating one video signal by synthesizing plural images, and a high vision monitor 4 for displaying the video signal outputted from this controller 3, and constituted so that plural images can be displayed simultaneously on this monitor screen.

Description

[Detailed description of the invention]

0001

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to an electronic endoscope system that displays output signals from a plurality of image sensors on a high-definition monitor.

0002

2. Description of the Related Art In recent years, endoscopes have come into widespread use in the medical and industrial fields. Recently, electronic endoscopes with a built-in image sensor at the distal end of the elongated insertion tube have been put into practical use, and an electronic endoscope system that processes image signals obtained by photoelectric conversion using the image sensor and displays them on a monitor. is also popular.

For example, in Japanese Patent Application Laid-open No. 189122/1989,
An electronic endoscope system is disclosed that can be used as either a field-sequential electronic endoscope or a simultaneous electronic endoscope. On the other hand, there is also a proposal to incorporate a plurality of imaging devices into an electronic endoscope so as to be able to obtain three-dimensional images. In order to improve the insertion operation and diagnostic functions of an electronic endoscope, it is desirable to be able to display multiple images on the same screen.

0004

[Problems to be Solved by the Invention] However, in conventional systems, the resolution of the monitor used is low, so when two images are displayed simultaneously, the resolution of both images decreases, or the resolution of the images that can be displayed simultaneously is There were drawbacks such as the limited number of

The present invention has been made in view of the above-mentioned points, and it is possible to display video signals obtained by a plurality of image sensors on the same monitor screen while maintaining sufficient resolution, or to display many images simultaneously. The aim is to provide an electronic endoscope system that can

[0006]

[Means and effects for solving the problem] An electronic endoscope equipped with a plurality of image pickup devices, and each image signal obtained from the plurality of image pickup devices is synthesized to generate a video signal that can be displayed simultaneously on a high-definition monitor. By providing a signal processing means and a high-definition monitor for displaying the video signal output from the signal processing means, it is possible to simultaneously display images from multiple image sensors on the same screen without reducing the resolution. There is.

[0007]

DESCRIPTION OF THE PREFERRED EMBODIMENTS The present invention will be specifically described below with reference to the drawings. 1 to 3 relate to a first embodiment of the present invention, FIG. 1 shows the structure of the distal end side of the electronic endoscope in the first embodiment, and FIG. 2 shows the structure of the electronic endoscope system in the first embodiment. A schematic configuration is shown, and FIG. 3 shows an example of image display on a high-definition monitor. As shown in FIG. 2, the electronic endoscope system 1 of the first embodiment includes an electronic endoscope 2 that has a plurality of built-in image sensors, and an internal endoscope that has a built-in signal processing means. It consists of a endoscopic image control device (hereinafter simply referred to as a control device) 3 and a high-definition monitor 4 connected to this control device 3.

The electronic endoscope 2 is for use in the large intestine, for example, and has an elongated insertion section 5 as shown in FIG. (
Charge-coupled devices) 7a to 7e (three shown in FIG. 1) are housed therein. In other words, the direct viewing objective lens system 8a is adjusted such that the axial direction of the insertion portion 5 is aligned with or parallel to the optical axis direction
is attached, and a first CCD 7a is disposed at the imaging position of this direct-viewing objective lens system 8a, forming a direct-viewing type imaging system. This first CCD 7a is a direct viewing CCD, and its number of pixels is, for example, 1000 x 1000 (= 100
1,000,000) pixels. The number of pixels of other CCDs 7b to 7e is, for example, 375×375 (=141000)
It is a pixel.

The above-mentioned direct view type imaging system has a viewing angle of 150°, for example, and an observation depth of 3 to 100 mm. In addition to the above-mentioned direct-viewing imaging system, four side-viewing imaging systems are provided so that observations can be made in four side-viewing directions perpendicular to the direct-viewing direction. That is, objective lens systems 8b and 8c for upper viewing (abbreviated as UP) and lower viewing (abbreviated as DOWN) are installed, and CCDs 7b and 7c for UP and DOWN are arranged at their respective imaging positions. ing. In addition, objective lens systems for right viewing (abbreviated as RIGHT) and left viewing (abbreviated as LEFT) are arranged perpendicular to the plane of the paper in FIG. C.C.
D7d and 7e are provided.

The objective lens system 8 for UP and DOWN
Reference numerals b and 8c are wide-angle lenses, which have a viewing angle of, for example, 100° and allow observation in the UP and DOWN directions as well as their rear sides, and the observation distance is, for example, 3 to 50 mm. In addition, the RIGHT and LEFT lens systems also have a visual field of 10 mm, centered on the right and left viewing directions.
It is formed with a wide-angle lens having an angle of 0°, and the rear side of the right side and left side can also be observed. Note that the four side objective lenses 8b, 8c, etc. are provided on the same cross section, and the CC
D7b to 7e are also provided on the same cross section. (However, they do not necessarily have to be provided on the same cross section. Also, although omitted in FIG. 1, a light guide (not shown) is provided so that it can illuminate the direct view and four side view directions.) The CCDs 7i (i=a to e) are connected to drive circuits 9i as shown in FIG. 2, and image signals photoelectrically converted by each CCD 7i are read out by drive signals output from each drive circuit 9i, not shown. After being subjected to preprocessing processing, sample hold processing, A/D conversion processing, etc., it is temporarily stored in the image memory 11i.

The image signal data stored in each image memory 11i is input to the image synthesis circuit 12, and is subjected to signal processing for image synthesis so that the five images fit within the video signal for one frame of the high-definition monitor 4. After that, the signal is input to a video processing circuit 13 which converts it into a video signal that can be displayed on a high-definition monitor 4. Then, the high-definition video signal output from this video processing circuit 13 is input to the high-definition monitor 4, and as shown in FIG.
Five images captured by the CD7i are displayed on the monitor screen 4A of the high-definition monitor 4 at the same time.

In this embodiment, an endoscopic image 14a captured by the direct viewing CCD 7a is displayed in a large size in the center of the monitor screen 4A, and images captured by the UP and DOWN CCDs 7b and 7c are displayed on the right and left sides of this image 14a. Endoscopic image 1
4b, 14c and CCD7 for RIGHT and LEFT
Endoscopic images 14d and 14e taken at points d and 7e are displayed simultaneously. As can be seen from FIG. 3, each of the endoscopic images 14i has an octagonal shape with four corners cut out.

According to the first embodiment, since the high-definition monitor 4 is used as the image display means, even if images captured by a plurality of CCDs 7a to 7e are displayed simultaneously,
Compared to the conventional example, display can be performed with less reduction in resolution. Furthermore, according to this embodiment, since it is possible to observe from a wide angle in the side view direction, it is also possible to observe the folds of the inner wall of the large intestine while the direct-viewing imaging system is directed toward the large intestine tube. therefore,
The operation of changing the orientation for observation after insertion can be reduced. Furthermore, since images can be obtained not only in direct view but also in four side view directions, it is easy to insert the insertion section 5 smoothly without hitting the inner wall, and to guide the observation to the desired position and direction. becomes.

FIG. 4 shows an electronic endoscope system 21 according to a second embodiment of the present invention, FIG. 5 shows the distal end side of an electronic endoscope 22 in this system 21, and FIGS. 6 and 7 show display examples. show. This electronic endoscope 22 has a distal end 24 of an insertion section 23.
Inside the focal plane of the direct viewing objective lens system 25a is a lens C for normal observation.
A CD 26a is provided, and CCDs 26b and 26c are also provided at each imaging position of the UP and DOWN objective lens systems 25b and 25c. In other words, the tip portion 23 has 3
Two imaging systems are provided. 2 in these three imaging systems
Each imaging system is sensitive to a specific wavelength range. For example, spectral filters 28 and 29 are installed in the UP objective lens system 25b and the DOWN objective lens system 25c, respectively, to provide sensitivity to a specific wavelength range.

In this embodiment, the filter 28 is a visible light removal filter that allows only infrared light to pass through the CCD 26b, making it sensitive only in this infrared region. On the other hand, the filter 29 is a spectral filter that passes only green wavelengths, and the CCD 26c is sensitive only to green wavelengths. Note that the CCD 26a is configured to take images in the normal visible range. Generally, when observing the inside of the body through an endoscope, infrared light observation is essential for observing blood vessels on the mucous membrane, and green light observation is essential for observing the contours of the mucous membrane in detail. is considered useful.

As described above, a system 21 shown in FIG. 4 is constructed using the electronic endoscope 5 equipped with an imaging system that enables an observation function in a specific wavelength range. Since the filters 28 and 29 are provided as shown in FIG. 5, the CCD 26b' in FIG.
5) is sensitive to infrared light, and the CCD 26c' (CCD 26c in FIG. 5 with a filter 29 added) is sensitive to green light.

The CCDs 26a, 26b', and 26c' are each input to a video processor 31j (j=a to c), where each signal is processed to generate a video signal. The video signal output of each video processor 31j is input to the display position selection circuit 32. This display position selection circuit 32 is constituted by a video memory, and can arbitrarily change the display position and display angle of view by changing the writing and reading timings to the video memory using a control signal 33.

The video signal output of the display position selection circuit 32 is a high-definition video signal output, which is input to the high-definition monitor 34 and displayed. FIG. 6 is an example of displaying images on the high-definition monitor screen 34A according to the second embodiment, where the central image 35a is an image captured by the CCD 26a for normal light observation, and the image 35b to the right of this image 35a is the CCD 26b'. The image 35c on the left is a green light image obtained by the CCD 26c'.

FIG. 7(a) shows a case where two images are displayed on the high-definition monitor screen 34A. This monitor screen 34A has an aspect ratio (ratio of vertical and horizontal display sizes)
is approximately 9:16, and the images 36a and 36b having the same angle of view are displayed on the left and right sides of the monitor screen 34A with center division. The selection setting of the display mode according to FIG. 6 or 7 is as follows.
This can be done by the control signal 33, for example by the user making a selection with a display mode selection switch.

In FIG. 7(a), for example, image 3 on the left
6a is an image obtained using normal light, and the image 36b on the right is an image obtained using another specific wavelength. In a conventional NTSC format monitor, the aspect ratio of the screen 37 is 3:4, and when both have the same angle of view and are displayed without vignetting, the angle of view is small as shown in FIG. 7(b). A reduction or deterioration of the resolution due to the display is unavoidable, making it extremely difficult to view. On the other hand, in the second embodiment, since the display screen is horizontally long and the number of scanning lines is much larger, the display can be performed without reducing the resolution. Therefore, it is very effective for diagnosis.

FIG. 8 shows an electronic endoscope system 41 according to a third embodiment of the present invention. This system 41 includes an electronic endoscope 42 having two imaging systems, a control device 43 containing a built-in means for supplying illumination light to the electronic endoscope 42 and performing signal processing, and High-definition monitor 4 that displays the output high-definition standard video signal
It consists of 4.

[0022] In the electronic endoscope 42, light guides 45a and 45b are inserted into the elongated insertion portion, and the illumination light irradiated on the proximal end face is transmitted and emitted from the distal end face. That is, each lamp 46a, 46b in the control device 43
The illumination light emitted from the lenses 47a and 47
The light is focused at the opening 49 of the light-shielding blade members 48a and 48b.
a, 49b to light guides 45a, 45b, respectively.
It is irradiated to the end face of the hand side. And light guide 45
a, 45b, and is emitted from the tip surface to the subject 50 in front.

The affected area, etc., illuminated by the illumination light emitted from the distal end surfaces of the light guides 45a, 45b is illuminated by the photoelectrons of the CCDs 52a, 52b disposed on the focal planes of the objective lenses 51a, 51b attached to the distal ends. An image is formed on the conversion surface and photoelectrically converted. Each CCD 52a, 52b has a processor 53a, which serves as a signal processing means in the control device 43,
53b via signal lines, and the photoelectrically converted image signals are each subjected to signal processing and converted into video signals, which are input to the display position selection circuit 54. This display position selection circuit 54 allows the two CCDs 5 to
The images captured by 2a and 52b are converted into a video signal that is synthesized into one image, and output to the high-definition monitor 44, and on this monitor screen 44A, for example, two images 55a and 55b are displayed at the same angle of view. displayed on the left and right.

Each output of the processors 53a and 53b (
For example, the brightness signal output) are the dimming circuits 56a and 5, respectively.
6b, each generates a dimming signal and drives the dimming control rotary solenoids 57a, 57b.
The light is automatically adjusted so that the amount of illumination light supplied to the light guides 45a and 45b through the light guides 45a and 49b becomes an appropriate amount. In other words, the dimming circuits 56a and 56b operate during one frame period, for example.
The luminance signal is integrated, the level of the integrated value is compared with a reference level, and the light-shielding blade member 48a,
The rotation direction of 48b is controlled.

[0025] Light control unit 5 including the light shielding blade member 48a
8a is as shown in FIG. As shown in FIG. 9, the base end of the arm of the blade member 48a is connected to a solenoid 57.
It is attached to the rotation drive shaft of a and rotates in the direction of arrow A or B (
(rotation) is possible. Therefore, when the light guide 45a is rotated in the direction of arrow A from the state shown in FIG. 9, the amount of illumination light supplied to the proximal end surface of the light guide 45a decreases, and when it is rotated in the direction of arrow B, it increases. This rotation angle is controlled according to the amount of deviation from the reference level of the dimming circuit 56a or 56b, and the rotation direction differs depending on whether it is higher or lower than the reference level.
The output of a or 53b is controlled to be maintained at a level corresponding to the reference level, that is, the amount of illumination light toward the subject 50 is controlled to be a light amount suitable for constant observation. The other light control section 58b also has a similar configuration.

Since this embodiment has an automatic light control function, images 55a and 5 displayed on the monitor screen 44A
5b is an image with brightness suitable for diagnosis. Further, as in the previous embodiment, the two images 55a and 55b can be displayed at the same angle of view without reducing the resolution, which is convenient for diagnosis and the like. Note that stereoscopic observation may be made possible by displaying the two images 55a and 55b alternately in synchronization with liquid crystal glasses or the like.

FIG. 10 shows an electronic endoscope system 61 according to a fourth embodiment of the present invention. This embodiment is an embodiment for simultaneously obtaining both a simultaneous image and a frame-sequential image and displaying them on a monitor at the same time. This system 61 includes an electronic endoscope 62 equipped with a simultaneous type and a frame sequential type imaging system, and a control device 63 having a built-in means for supplying illumination light to the electronic endoscope 62 and performing signal processing. And this control device 6
3, and normal monitors 64B and 64C.

A light guide 65 is inserted into the elongated insertion portion of the electronic endoscope 62, transmits illumination light irradiated to the proximal end surface, and emits it from the distal end surface. That is, the illumination light emitted from the lamp 66 in the control device 63 is focused by the lens 67 and irradiated onto the incident end surface of the light guide 65 via the rotary filter 69 which is rotationally driven by the motor 68. This rotary filter 69 has R as shown in FIG.
, G, B filters 69R, 6 that pass through them, respectively.
9G and 69B, and a transparent portion 69T provided between adjacent filters.

Therefore, through this rotary filter 69,
As shown in FIG. 12, the illumination light irradiated onto the end surface of the light guide 65 (or the illumination light emitted from the output end surface of the light guide 65 toward the subject 71 side) includes R light, transmitted light (
In other words, the illumination light includes white light), G light, transmitted light, B light, and transmitted light. Since the illumination light passing through the light transmitting portions 69T becomes white light, images are captured by a simultaneous imaging system during the illumination period through each light transmitting portion 69T. On the other hand, images are taken using a frame-sequential imaging system during the R, G, and B light periods. In this embodiment, for example, the period from irradiation of the R light to irradiation by the transparent portion 69T is set to 1/60 second, as shown in FIG.

The object 71 illuminated with the illumination light is imaged by objective lenses 72a and 72b attached to the distal ends on CCDs 73a and 73b disposed at respective imaging positions, and is photoelectrically converted. A mosaic filter 74 is disposed in front of the photoelectric conversion surface of the CCD 73a, and optically separates colors for each pixel, for example. These CCD73a,
The photoelectric conversion output of 73b is provided by a simultaneous processor 75.
a and a frame-sequential processor 75b, and are converted into video signals. The video outputs of the processors 75a and 75b are input to the display position selection circuit 76, where the images are combined, converted into a high-definition standard video signal, and output to the high-definition monitor 64A, so that two images are displayed simultaneously on the monitor screen. Ru.

The video outputs of the simultaneous processor 75a and the frame sequential processor 75b are input to separate monitors 64B and 64C, respectively, to display images captured by the simultaneous imaging system and the frame sequential imaging system, respectively. . The frame-sequential CCD 73b accumulates charges during the RGB irradiation timing period, and executes charge readout during the timing period of the transparent portion 69T. The simultaneous CCD 73a accumulates charges during the timing period of the transparent portion 69T, and executes charge readout during the timing period of RGB irradiation.

In order to operate at this timing, a rotation sensor 77 is arranged opposite to the rotary filter 69, and detects the rotation period and reference position of the rotary filter 69 rotated by the motor 68. Light-G-Translucency-B-
The switching timing of the transparent light -R... is detected, and a detection signal thereof is output to a CCD drive circuit (not shown) in the processors 75a, 75b, thereby switching the charge storage and readout mode. Then, on the high-definition monitor 64A, an image 79a captured by the simultaneous imaging system and an image 79b captured by the frame sequential imaging system are displayed side by side at the same angle of view.

Conventionally, the frame-sequential type has caused color misregistration for moving subjects, while the simultaneous type has been fundamentally accompanied by insufficient resolution. According to this embodiment, the observer can arbitrarily observe any image depending on the required characteristics of diagnosis using an electronic endoscope. FIG. 13 shows the distal end side of an electronic endoscope 81 in a fifth embodiment of the present invention, and FIGS. 14 and 15 show a front view and a sectional view. In this embodiment, optical images formed by two objective optical systems 83a and 83b for direct viewing and side viewing on the UP side are formed adjacent to each other on one CCD 82.

As shown in FIG. 13, a forceps port 85 is provided in the axial direction of the distal end component 84 constituting the distal end portion 83 of the insertion section, and the exit side of this forceps port 85 becomes a widened distal end opening 85a. A forceps raising stand 86 is attached to the inside of this opening 85a, and by pulling a raising operation wire 87, the forceps can be raised from the position shown by the solid line to the position shown by the dotted line. In addition, as shown in FIG. 15, inside the insertion section are a first light guide 88a and a second light guide for direct viewing (illumination).
A light guide 88b is inserted therethrough, and a side viewing light guide 89 is also inserted therethrough.

The front end surfaces of the light guides 88a and 88b are provided with first and second direct-view illumination windows 90a and 9 shown in FIG.
Each lighting window 90a, 90b is fixed opposite to the back of 0b.
Illumination light is emitted from the front. These lighting windows 90a
, 90b, a direct-view observation window 91 is provided, and a direct-view objective optical system (not shown) is attached to a direct-view objective lens frame 92. An air/water supply nozzle 93 is provided to face the observation window 91, and this nozzle 93 is attached to the tip of an air/water supply tube 93a (see FIG. 15).

As shown in FIG. 13, the side-viewing light guide 89 has a bent end side and a notched side surface (
In other words, it is fixed so as to face upward), and a side-view illumination lens 95 is provided in a side-view illumination window 94 provided in front of the distal end surface.
is attached, and illumination light is emitted upward through this lens 95. Adjacent to this illumination window 94, a side view observation window 96
is formed and constitutes the side-viewing objective optical system 97.
a is installed. Opposing this lens 97a,
A prism (roof prism) 97b is disposed, and a lens 9 is disposed opposite to the prism 97b in the axial direction of the insertion portion.
7c and 97d are attached to the objective lens frame 98.

At the imaging position of this side-viewing objective optical system 97,
A photoelectric conversion surface of the CCD 82 is provided. In this case, as shown in FIG. 15, the CCD 82 has a horizontally long image area 8 with a horizontal to vertical ratio of 16:9.
Images formed by the two objective optical systems are formed adjacent to each other on 2a so that the heights of both imaging rays are equal. Note that the viewing angles of the direct-viewing and side-viewing objective optical systems are set to, for example, 140° and 80°, respectively. The CCD 82 and a CCD peripheral circuit board 100 are connected by a terminal 99 on the back surface of the CCD 82, and the CCD peripheral circuit board 100 is connected to each signal line 102 of the bundled signal line 101.

Adjacent above this bundled signal line 101,
An air/water supply tube 103 for side viewing is inserted, and an air/water nozzle 104 attached to the tip of this tube 103 faces the outer surface of the side viewing observation window 96 so as to be able to clean the surface of the lens 97a. . In addition, as shown in FIG. 15,
The raising operation wire 87 passes through the space between the lens frames 92 and 98 and is inserted into the guide pipe 105. still,
106 indicates a channel tube.

In this embodiment, by using the horizontally long CCD 82, the function is substantially the same as when two CCDs are provided. The photoelectric conversion output of the optical image formed on the CCD 82 is processed by a signal processing system (not shown), and two images are displayed on the high-definition monitor screen 34A as shown in FIG. 7(a), for example. It has become. The side viewing light guide 89 passes along the left side of the CCD 82 and the lens frame 98 as shown in FIG.
As shown in FIG.
Its tip is oriented parallel to the optical axis of the lens. The electronic endoscope 81 in this embodiment is mainly suitable for use in the stomach.

FIG. 16 shows an electronic endoscope system 111 according to a sixth embodiment of the present invention, and this system 111 is capable of obtaining a fluorescent image. This system 111 includes an electronic endoscope 112, a light source device 113 that supplies illumination light to this electronic endoscope 112, a signal processing device 114 that processes signals for the imaging system of this electronic endoscope 112, and a signal processing device 114 that processes signals for the imaging system of this electronic endoscope 112. It is composed of a high-definition monitor 115 that displays the video signal output from the processing device 114.

The electronic endoscope 112 has an elongated insertion section 1.
16, and an operating section 1 connected to the rear end of the insertion section 116.
17 and a universal cable 118 extending to the outside from this operating section 117, and a connector 119 provided at the end of this cable 118 can be detachably attached to the light source device 113. A signal cable 121 further extends from this connector 119, and a connector 122 attached to the end of this signal cable 121 can be attached to the signal processing device 114. The light source device 113 includes a first light source for normal observation.
A lamp 124 and a second lamp 125 for excitation are provided, and first and second lamp lighting circuits 126 and 1 are provided, respectively.
It is lit by the power supplied from 27.

These first lamp 124 and second lamp 1
A mirror 128 is disposed in front of the optical path of 25, and this mirror 128 is driven by a mirror drive circuit 129. For example, in the state of FIG. 16, the illumination light of the second lamp 125 (
The function is that the excitation light) is reflected by the mirror 128, passes through the lens 131 and the shutter 132, and then passes through the light guide 133.
The light is irradiated onto the end face of the incident side. This light guide 133 is inserted through the cable 118 and the insertion portion 116, transmits the illumination light supplied to the end face on the incident side, and the transmitted illumination light is emitted forward from the end face on the distal end side.

The mirror 128 in the state shown in FIG.
The mirror 128 is rotated as shown by the dotted line.
can be rotated by 45 degrees. When rotated in this manner, the illumination light from the first lamp 124 is supplied to the light guide 133. This control circuit 134 controls the shutter 13 via a solenoid 132a.
It also controls the opening and closing of 2. Furthermore, when the dual-screen display switch 135 provided in the signal processing device 114 is turned on, the control circuit 134 changes from displaying the normal observation image under the illumination light of the first lamp 124 to also displaying the fluorescence observation image. It is designed to control the

The CCD 137 disposed at the imaging position of the objective lens 136 provided at the distal end of the insertion section 116 receives signals via the signal line inside the insertion section 116, the signal line inside the universal cable 118, and the signal line inside the signal cable 121. CCD driver 138 and switch circuit 139 of processing device 114
is connected to. Then, by applying a CCD drive signal from the CCD driver 138, the photoelectrically converted signal is read out and passed through the switch circuit 139 to the first memory 1.
41 or second memory 142. The switch 139 and the first and second memories 141 and 142 are controlled by a control circuit 143.

The outputs of the first and second memories 141 and 142 are output to the high-definition monitor 115 via a display position select circuit 144. Note that the display position selection circuit 144 receives control signal 1 from the operation of the display control console 145.
46, it is possible to control the selection operation of the display position displayed on the high-definition monitor 115 in the same way as described with reference to FIG. Note that a bending operation knob 147 is provided on the operation section 117 of the electronic endoscope 112. In this system 111, when the dual screen display switch 135 is not turned on, only the normal observation image is displayed on the high-definition monitor 115, and when this switch 135 is turned on, the fluorescent image is displayed together with the normal observation image.

Next, the operation of this system 111 will be explained with reference to FIG. The dual screen display switch 135 is shown in FIG.
When the mirror 128 is OFF as shown in (a), the mirror 128 is in the position shown by the dotted line in FIG.
3 is supplied with illumination light from the first lamp 124 as shown in FIG. 17(b). Under this illumination light, the CCD
137 is stored in the first memory 141 via the switch circuit 139, and the image signal stored in the first memory 141 is displayed on the monitor 115. In this case, the image signal is displayed as shown in FIG. 17(d). It becomes a normal image.

Note that in this state, the shutter 132 is
As shown in 7(c), it is always open. In this normal image display state, as shown in FIG. 17(a), switch 1
35 is turned on, the control circuit 134 detects this signal and controls the mirror drive circuit 129 to rotate the mirror 128 to the position shown by the solid line in FIG. Then, the first lamp 124 is blocked by this mirror 128, while the illumination light (excitation light) of the second lamp 125 is reflected by the mirror 128,
The light is supplied to the light guide 133.

That is, as shown in FIG. 17(b), the illumination lamp in this state is switched to the second lamp 125. At this time, the control circuit 143 in the signal processing device 114 controls the first
The memory 141 is set to a write-protected state, and the first memory 141
The normal images stored in are repeatedly output, and the monitor 115 changes from a moving normal image to a still image normal image. When the second lamp 125 is illuminated for a predetermined excitation period T, the shutter 132 is closed and the illumination is interrupted as shown in FIG. 17(c). (After this interruption, the signal from the CCD 137 is once discarded.) Therefore, the image captured by the CCD 137 after this closure is a fluorescent image, and the signal output from the CCD 137 is controlled by the switch switched by the control circuit 143. The data is stored in the second memory 142 via the circuit 139.

The images read out from the first memory 141 and the second memory 142 are sent to the display position selection circuit 14.
After step 4, image synthesis processing is performed, and two images, that is, a normal image and a fluorescent image, are displayed on the monitor 115 at the same time. Then, t seconds after the switch 135 is turned on, the mirror 1
28 returns to the position shown by the dotted line in FIG.
32 is open. At the same time, the switch circuit 139 is switched, and the image captured under the illumination of the first lamp 124 is stored in the first memory 141, and the normal image becomes a moving image. At this time, the second memory 142 is write-protected, the image stored immediately before is repeatedly output, and the fluorescent image becomes a still image.

Thereafter, each time the dual screen display switch 135 is turned on, the above sequence is repeated and the fluorescent image is updated. Note that if the first lamp 124 has sufficient energy as an excitation light source, it can perform the same function without providing the second lamp 125 (in this case, the mirror 128 and its driving circuit 129 is also not required). FIG. 18 shows a system 151 according to a seventh embodiment of the present invention. This system 151 is designed to obtain normal color images and biological function images.

[0051] This system 151 includes an electronic scope 152 capable of infrared observation, and a system capable of obtaining various wavelength range images ranging from the visible range to the infrared range in order to obtain images of blood flow and hemoglobin oxygen saturation as biological function images. By using an endoscope device 153 that has a built-in light source means and signal processing means, and performing inter-image calculations on various wavelength region images obtained by this endoscope device 153, a hemoglobin distribution image and hemoglobin oxygen saturation can be obtained. A processing unit 154 performs arithmetic processing to obtain an image, and both the image processed by this processing unit 154 and the normal color image from the endoscope device 153 are inputted to a high-definition (HDTV).
It is composed of a multi-high resolution frame memory device 156 that combines images so that they can be output to a monitor 155, and an HDTV monitor 155.

[0052] The above multi-high resolution frame memory device 1
56 is configured as shown in FIG. Endoscope device 153
C receives image data from and controls the entire device.
A PU circuit 157, a control logic circuit 160 that controls the first and second frame memory circuits 158 and 159 under the control of the CPU circuit 157, and a memory circuit 161 that processes image data input from the processing unit 154. A first frame memory circuit 158 for displaying the image data of this memory circuit 161 on the HDTV monitor 155, and an interface circuit 162 for inputting the image data output from the endoscope device 153 as a digital signal. HDT input image data
A data conversion circuit 163 that converts the image data of the display size for HDTV and the image data of the endoscope device 153
A second frame memory circuit 159 for displaying on the monitor 155, and a D/A conversion circuit 164 for synthesizing digital image signals output from these frame memory circuits 158 and 159 and converting them into analog HDTV signals for display. configured.

The first and second frame memory circuits 15
8 and 159 are connected to the control logic circuit 160 via a system bus. Further, these frame memory circuits 158 and 159 are connected to a memory circuit 161 via a DMA bus. Further, these frame memory circuits 158 and 159 are connected to the D/D via the image bus.
It is connected to the A conversion circuit 164. Next, the operation of this embodiment will be explained.

[0054] Electronic scope 1 capable of imaging up to the infrared region
52 is a combination of wavelengths necessary for calculating the light absorption characteristics of hemoglobin, which is a pigment in living bodies, in the wavelength range illuminated by endoscope device 153, in addition to normal color images in living bodies. Then, various wavelength range images necessary for calculating the pigment concentration of hemoglobin are obtained, and the endoscopic device 1
53.

Various wavelength domain images obtained by signal processing by the endoscope device 153 are subjected to inter-image calculations in a processing unit 154 to obtain a hemoglobin pigment density image and a hemoglobin oxygen saturation image. Various biological function images processed by the processing unit 154 are input to a multi-high resolution frame memory device 156. The input biological function image is reduced in size in the CPU circuit 157 and transferred to the memory circuit 161, and from this memory circuit 161 is transferred to the first frame memory circuit 158 via the DMA data bus.
will be forwarded to.

On the other hand, normal moving images input from the endoscope device 153 are converted into digital data by the interface circuit 162, and the data is converted by the data conversion circuit 163 so that it can be displayed on the HDTV monitor 155. Ru. The converted image data is transferred from the second frame memory 159 to the image bus under control from the control logic circuit 160 via the system bus. The D/A conversion circuit 164 synthesizes the image data transferred to the image bus and outputs it as analog image data. The output image data is displayed on the monitor 155 as shown in FIG.
It will be displayed like this.

For example, a normal color image 166A is displayed on the right side of the screen 165, and a blood flow image 166 representing changes in hemodynamics due to hemoglobin distribution is displayed on the left side as biological function information.
B and hemoglobin oxygen saturation image 166C are displayed at the same time for easy comparison with normal images. According to this embodiment, a color image 166A for normal observation and images 166B of hemodynamic changes due to hemoglobin distribution and hemoglobin oxygen saturation as biological function information are displayed on the same high-resolution display device. 166C at the same time, it is possible to obtain information such as the state of congestion in the normal image observation state than in the conventional example, and furthermore, it is possible to compare and contrast the normal observation images at the same time, and various images can be displayed as often as before. There is no need to switch between the two, making it easy to compare and contrast, which has the effect of improving diagnostic ability.

FIG. 21 shows system 1 of the eighth embodiment of the present invention.
71 is shown. This system 171 includes a stereoscope 172 that has two built-in image sensors on the left and right sides (has two light receiving sections) and can measure length, and a stereo endoscope that has a light source that illuminates the subject and outputs left and right images. device 173, a shape processing unit 174 that measures the shape of a designated region using left and right image data with parallax obtained from the stereo endoscope device 173; The left and right images with parallax and the shape information of the subject processed by the shape processing unit 174 are transferred to the HD
It is composed of a multi-high resolution frame memory device 176 that displays on a TV monitor 175, and an HDTV monitor 175 that displays images synthesized by the multi-high resolution frame memory device 176.

As shown in FIG. 22, the configuration of the high resolution frame memory device 176 is the same in block configuration as that shown in FIG. 19. Next, the operation of this embodiment will be explained. Stereoscope 17 capable of capturing left and right images with parallax
2 captures an image of the region to be subjected to shape measurement, and the stereo endoscope device 173 sends two types of image signals to the shape processing unit 1.
74 and a multi-high resolution frame memory device 176.

As previously disclosed by the applicant, the shape processing unit 174 has a function of calculating the shape data of the object to be observed from two types of images with parallax. Calculate the shape data of the part. Using image signals input by the shape processing unit 174 and the stereo endoscope device 173, an image is displayed on the HDTV monitor 175 in the same manner as in the seventh embodiment. Here, on the HDTV monitor 175, the stereoscope 1
23(a) when capturing an image of the object to be observed using 72.
Left and right images 177a and 177b with parallax output from the stereo endoscope device 173 are displayed on the same monitor screen 175A as shown in FIG.

By displaying the images on the same monitor screen 175A, it becomes easy to confirm whether the image of the object to be observed for shape measurement is within both the left and right viewing angles. When the object to be observed is captured within both angles of view, the image of the object to be observed is frozen by pressing a freeze button provided on the operation section of the stereoscope 172 or the like. Regarding the parts that require shape measurement in the still left and right images, specify the part using the mouse, and the shape processing unit 174 calculates shape data about the range of polyps and lesions, as shown in FIG. 23(b). A still image with recorded shape data is displayed on the sub-screen 178, and a moving image of the region whose shape is being measured using the moving image from the stereo endoscope device 173 is displayed on the main screen 179.

[0062] Then, for example, at the bottom of the sub-screen 178, data calculated regarding the height H and width W of the polyp or the like is displayed. According to this embodiment, since the left and right images with parallax are displayed on the same monitor, the left and right images can be easily checked, resulting in improved operability. Furthermore, since endoscopic image examination can be performed together with quantitative measurement values such as shape data of the object to be observed, the size of the lesion site can be accurately examined, which has the advantage of improving diagnostic performance. In addition, by displaying the shape data from the previous inspection on the same monitor,
It becomes possible to quantitatively examine changes in the size of the region of interest.

FIG. 24 shows system 2 according to the ninth embodiment of the present invention.
01 is shown. Conventionally, by displaying an image obtained in the G wavelength region in monochrome when observing a color image, it has been possible to observe minute changes in the biological mucosal surface. In this case, a normal color image and an infrared image are switched and displayed. For this reason, direct comparison was difficult, so in this example, image signals in different wavelength regions were displayed simultaneously.
This makes it easy to compare and allows observation of everything from minute changes on the surface of the biological mucosa to changes deep within the biological mucosa, thereby improving diagnostic ability.

As shown in FIG. 24, this system 201
consists of an infrared electronic scope 202 inserted into a living body, an endoscope device (main body) 203 that enables infrared observation, and records endoscopic image signals. Image file device 204, image data from the image file device 204, and endoscope device main body 2
A multi-high resolution frame memory device 205 that synthesizes image data from 03 and displays it at a designated monitor position, and an HD
It is composed of a TV monitor 206.

Multi-high resolution frame memory device 205
is configured as shown in FIG. Image file device 2
A CPU circuit 207 that receives image data from 04 and controls the entire device, a control logic circuit 210 that controls the first and second frame memory circuits 208 and 209 by the control 207 of this CPU circuit, and an image file device 204. a first frame memory circuit 208 for displaying the image data in the memory circuit 211 on the HDTV monitor 206; An interface circuit 212 for inputting image data as a digital signal, a data conversion circuit 213 for converting the input image data into image data of a display size for HDTV, and an interface circuit 213 for converting the input image data into image data of display size for HDTV, and converting image data from the endoscope device 203 to the HDTV monitor 206. a second frame memory circuit 209 for displaying on the frame memory circuit 209;
8 and 209, and a D/A conversion circuit 214 that synthesizes the digital image signals outputted from 8 and 209 and converts it into an analog HDTV signal for display.

As shown in FIG. 26, a normal image (visible moving image) 215, an infrared image 216, and a G image 217 can be displayed simultaneously on the monitor screen 206A. Next, the operation of this embodiment will be explained. The biological mucous membrane is observed using an infrared electronic scope 202 inserted into the biological body. Here, when infrared observation is selected on the endoscope main body 203 for the purpose of observing the hemodynamics in the biological mucosa, the illumination light of the endoscope main body 203 becomes infrared light, and the animation shown in FIG. 26 The display area of the image 215 becomes an infrared image rather than a visible image.

[0067] Next, by intravenously injecting ICG, the pigment concentration in the blood in the biological mucosa fluctuates, and areas with fast blood flow,
The pigment concentration increases quickly after intravenous ICG injection. Therefore, the infrared image in the region of interest is frozen and recorded by the image file device 204. The recorded infrared still images are input to a multi-high resolution frame memory device 205. For example, when this recording is finished, the infrared electronic scope 2
02 returns from the infrared observation mode to the normal observation mode. When the mode is restored, the monitor screen 206A displays the infrared image 216 as a still image on the upper left side and the normal image 215 as a large moving image on the right side, as shown in FIG. Then, suppose that the region of interest is observed and a mode for observing with a G image, which allows observation of the fine structure of the biological mucosal surface unlike infrared light, is specified.

Multi-high resolution frame memory device 205
In response to instructions from the endoscope main body 203 to display moving images of normal observation images and G images, the main display is a normal moving image as shown in FIG. 26, and a G image that clearly displays the fine structure of the mucosal surface.
Performs operations to display moving images. That is, the control logic circuit 210 operates to display only the G image of the normal image data in the display area of the G image among the normal images input to the second frame memory circuit 209. Further, the normal observation video inputted from the endoscope device 203 is transmitted to the interface circuit 21.
2 is converted into digital data by data conversion circuit 2.
At step 13, the data is converted so that it can be displayed on the HDTV monitor 206.

The converted image data is transferred from the second frame memory circuit 209 to the image bus under control from the control logic circuit 210 via the system bus. The D/A conversion circuit 214 synthesizes the image data transferred to the image bus and outputs it as analog image data. On the other hand, the infrared still image input from the image file device 204 is reduced in size in the CPU circuit 207 and transferred to the memory circuit 211.
11 to the first frame memory 20 via the DMA data bus.
Transferred to 8. The image data outputted via the D/A conversion circuit 214 is displayed on the monitor 206 as shown in FIG.

According to this embodiment, an infrared image showing submucosal information in a region of interest of a biological mucosa, a G image showing a fine structure of the surface in the region of interest, and a moving image under normal observation light are displayed on the same monitor. This has the effect of improving operability, since the region of interest can be easily compared without switching between different images.

FIG. 27 shows a system 401 according to a tenth embodiment of the present invention. This system 401 has a CCD (
An infrared electronic scope 402 that can image even in the infrared light region by removing an infrared cut filter (not shown), and a first light source 40 connected to this infrared electronic scope 402
3, a second light source 404 connected to the infrared electronic scope 402, and a camera control unit (CCU) 40 that visualizes image data from the infrared electronic scope 402.
5, and an image file device 40 for recording endoscopic image signals.
6, a multi-high resolution frame memory device 407 that combines image data from the image file device 406 and image data from the camera control unit 405 and displays it at a designated monitor position, and an HDTV monitor device 408.
It consists of

FIG. 28 shows the configuration of a first light source 403 and a second light source 404 connected to an infrared electronic scope 402. In FIG. 28, a first light source 403 includes a lamp power source 410 for driving a lamp, and an ultraviolet light amount range, a visible light amount range, and an infrared light amount range for illuminating an object to be observed using power from this power source 410. A xenon lamp 411 that generates light with a wide range of wavelengths, and a lens 412 that focuses the illumination light generated by the xenon lamp 411.
and an output connector 41 that connects the electric signal from the electronic scope 402 and the illumination light from the light source to the electronic scope 402.
3, and a rotating filter 41 that separates illumination light in color in time series.
4, a drive motor 415 that rotates this rotary filter 414, and a drive circuit 41 that drives this motor 415.
6, a shutter means 417 that cuts illumination light when the scope 402 is removed from the output connector 413, an aperture means 418 that adjusts the amount of illumination light based on an exposure control signal from the camera control unit 405, and this aperture means. The exposure control circuit 419 drives the exposure control circuit 418.

Furthermore, this first light source 403 controls a communication circuit 420 that communicates with the camera control unit 405 via the scope 402, and an exposure control circuit 419 and a drive circuit 416 based on information from the camera control unit 405. system controller (system controller) 421 and camera control unit 4
05, and a light source connector 422 for inputting a synchronization signal and information necessary for adjusting the light amount.

The second light source 404 has almost the same configuration as the first light source 403, except for the different parts from the first light source 403.
The rotating filter 414' has a rotating filter 414' set to have different spectral transmittance characteristics. The rest has the same configuration as the first light source 403, and the same members are given the same reference numerals and their explanations will be omitted. In addition, electronic scope 4
02 are connected to the output connectors 413 of the first light source 403 and the second light source 404 via an optical path switching device 424 and a signal switching device 425, respectively. Switching between these devices 424 and 425 is controlled by an output signal from camera control unit 405. The operation of this embodiment will be explained below.

When performing normal observation, the infrared electronic scope 402 is separated into colors by the rotating filter 414 of the first light source 403, so the optical path switching device 424 and the signal switching device 425 is connected to the first light source 403. The infrared electronic scope 402 converts the illumination light, which has been color-separated in time series by the rotating filter 414, into normal RGB in the camera control unit 405.
The image is recorded in the image file device 406 as a color image.

This RGB image synchronization signal is input from the camera control unit 405 to the system controller 421 of the first light source 403 via the light source connector 422. The system controller 421 synchronizes the RGB rotary filter 414 with the RGB image by driving the motor 415 using the drive circuit 416 in synchronization with the image readout of the infrared electronic scope 402 based on the synchronization signal of the RGB image. Further, the output signal of the camera control unit 405 is outputted to the HDTV monitor device 408 via the multi-high resolution frame memory device 407 to display a color image.

On the other hand, in order to obtain an image using illumination light from the second light source 404, the infrared electronic scope 402 is controlled by a control signal from the camera control unit 405.
When the infrared electronic scope 402 is connected to the second light source 404 using the optical path switching device 424 and the signal switching device 425,
It becomes possible to obtain an image with the illumination of the second light source 404. The second light source 404 differs from the first light source 403 in the configuration of a rotating filter 414, and performs color separation in the ultraviolet light amount range and infrared light amount range instead of the normal visible light amount range.

The color-separated image is converted into an image by the camera control unit 405, and the level of the image is changed from the camera control unit 405 to the infrared electronic scope 40.
The light is input from the output connector 413 to the second light source 404 via the second communication line. The input image level signal is input to the system controller 421 via the communication circuit 420. The system controller 421 controls the aperture means 41 by transmitting the image signal level obtained from the communication circuit 420 to the exposure control circuit 419.
The camera control unit 405 adjusts the amount of drive of the camera control unit 405 to obtain an appropriately exposed image.

For example, as shown in FIG. 29, R, G, and B images 432, 433, and 434 read from the image file device 406 are displayed on the upper side of the monitor screen 431, and ultraviolet images are displayed on the lower side. An image 435 and two infrared images 436 and 437 are displayed simultaneously. According to this embodiment, it is possible to observe not only changes in the normal visible range image in the region of interest, but also changes in the ultraviolet light amount range and infrared light amount range, thereby making it possible to observe changes in natural fluorescence and progress within the biological mucosa. Being able to observe changes, etc. on the same monitor has the effect of improving diagnostic ability.

[0080] As another example of the combination of the light source for normal observation and the light source for special observation, the light source for special observation is 805n for calculating the intravenously injected ICG dye concentration.
By calculating and displaying the logarithmic difference between images obtained with filters with center wavelengths of m and 900 nm, diagnosis using normally visible color images and blood flow velocity in living bodies can be easily monitored. The biological function information calculated based on the time-series changes in the dye concentration may be displayed on the same monitor. Further, in the light source for special observation, a filter for calculating a hemoglobin distribution image and a hemoglobin oxygen saturation image may be provided. Further, two normal color images of R, B, and B, and a fall-through image such as a G image or an IR (infrared region) image may be displayed on the monitor screen at the same viewing angle.

FIG. 30 shows a system 501 according to an eleventh embodiment of the present invention. Conventionally, ICG was intravenously injected during infrared observation, and the area of interest was observed chronologically using infrared images, and the lesion was then switched to visible images to comprehensively diagnose the lesion. Furthermore, in electronic endoscopes, still images of regions that require recording of the observed region are recorded in an image file device. In addition, still images were displayed on a small screen. Furthermore, during endoscopy,
After checking the images of the area of interest from last time, an endoscopy was performed. Therefore, it was not easy to compare
In this embodiment, when observing the current image, it is possible to easily compare the current image with a still image with a time difference, thereby realizing an HDTV display device that can improve diagnostic performance based on chronological changes in the observed region. It is.

In this example, in order to facilitate time-series infrared observation during infrared observation, the time-series infrared images after intravenous ICG injection are displayed in chronological order as still images. The purpose is to facilitate observation of the hemodynamics of living mucous membranes by temporal changes in ICG dye concentration and changes in dye concentration between different sites, thereby improving diagnostic ability.

Next, this system 501 will be explained. As shown in FIG. 30, this system 501 consists of an electronic scope 502 that is inserted into a living body, an endoscope main body 503 that enables infrared observation, and a light source and a camera control unit. This endoscope device main body 503 instructs the image recording interval, and an image file device 504 that records endoscopic image signals, image data from this image file device 504, and image data from the endoscope device main body 503. It is composed of a multi-high resolution frame memory device 505 that combines image data and displays it at a designated monitor position, and an HDTV monitor device 506. The image file device 504 records image data at specified intervals during observation after intravenous ICG injection. On the other hand, the multi-high resolution frame memory device 505 is configured as shown in FIG.

A CPU circuit 510 that receives image data from the image file device 504 and controls the entire device, and a control logic that controls the first and second frame memories 511 and 512 under the control of this CPU circuit 510. A circuit 513 , a memory circuit 514 for processing image data input from the image file device 504 , and an image stored in the memory circuit 514 are transmitted to the HDTV monitor device 5 .
06, and an interface circuit 51 for inputting image data output from the endoscope main body 503 as a digital signal.
5, a data conversion circuit 516 for converting input image data into table-sized image data for HDTV, a second frame memory 512 for displaying image data of the endoscope device on an HDTV monitor, and a first and a D/A conversion circuit 517 that combines digital image signals output from the second frame memories 511 and 512 and converts them into analog HDTV signals for display.

Next, the operation of this embodiment will be explained. The biological mucous membrane is observed using an electronic scope 502 inserted into the biological body. Here, when infrared observation is selected with the endoscope device for the purpose of observing hemodynamics in the biological mucosa, the illumination light of the endoscope device becomes infrared, and the current video on the monitor screen 520 shown in FIG. 32 is displayed. The display area of the image 521 becomes an infrared image rather than a visible image.

[0086] Next, by intravenously injecting ICG, the pigment concentration in the blood in the biological mucosa fluctuates, and areas with fast blood flow,
The pigment concentration increases quickly after intravenous ICG injection. Here, at the timing when ICG is intravenously injected from the endoscope device 503 during the infrared observation mode, a start signal is input to the image file device 504, and infrared still images are stored in the image file at preset intervals. It is recorded on the device 504. The multi-high resolution frame memory device 505 receives moving images from the endoscope device 503 and infrared images captured from the image file device 504 at preset intervals. The input infrared still image is reduced in size by the CPU circuit 510 and transferred to the memory circuit 514, and then transferred from the memory circuit 514 to the first frame memory 511 via the DMA data bus.

On the other hand, the infrared moving image input from the endoscope device 503 is converted into digital data by the interface circuit 515, and the data is converted into digital data by the data conversion circuit 516 so that it can be displayed on the HDTV monitor 506. converted. The converted image data is transferred from the second frame memory 512 to the image bus under control from the control logic circuit 513 via the system bus. The D/A conversion circuit 517 synthesizes the image data transferred to the image bus and outputs it as analog image data. The output image data is displayed on the monitor device 506 as shown in FIG. 32.

For example, the current moving image 521 is displayed on the right side of the monitor screen 520, and the time series of changes in ICG concentration in the mucous membrane after intravenous injection of ICG is displayed on the left side at fixed time intervals (10 seconds in this case). (eg, six) infrared images 522 are displayed simultaneously. By displaying the current moving image 521 and the time-series infrared image 522 after intravenous ICG injection on the same monitor in this manner, the amount of change in ICG concentration can be accurately determined. According to this embodiment, temporal changes in the pigment concentration of the biological mucosa and changes between regions are displayed simultaneously with the current moving image, so each image can be easily compared, and changes in hemodynamics in the biological mucosa are displayed simultaneously. can be observed accurately, which has the effect of improving diagnostic ability.

FIG. 33 shows a system 601 according to a twelfth embodiment of the present invention. This system 601 displays a plurality of still images recorded during an examination on the same monitor as the moving image currently being observed, and the system 501 shown in FIG.
When a release button provided on the electronic scope 502 outputs a release signal to the endoscope device 503, the endoscope device 503 outputs the release signal to the image file device 504. The image file device 504 is configured to record a still image based on this input release signal.

The recorded image signals are input to the multi-high resolution frame memory device 506, and are displayed on the same monitor 506 as normal moving images in the same display format as in the tenth embodiment in the order in which they are released. 34. For example, in the same case, by simultaneously displaying the current action image 611 and the released still image 612 on the monitor screen 610 shown in FIG.
This eliminates missing images and allows for easy comparison with other parts. In FIG. 34, 1 to 6 in the released images 612 indicate the order of release.

According to this embodiment, the image file device 5
Since the still images recorded in 04 are simultaneously displayed on the observation monitor 506, it is easy to check for omissions in recording and to compare other parts that are displayed as still images and the current image that is displayed as a moving image. Therefore, it has the effect of improving diagnostic ability. Figure 35
shows a display example of a monitor screen 701 in the thirteenth embodiment of the present invention.

As shown in this figure, the current image 702 and an image (previous image) 703 of the lesion or the same area discovered in the previous examination are created in an image file with the same size as the area currently being observed. The images are input from the device to a multi-high resolution frame memory device and displayed simultaneously on the screen of an HDTV monitor. By displaying in this way, even subtle changes in lesions can be identified without being overlooked, making it possible to improve diagnostic performance.

Next, a fourteenth embodiment of the present invention will be described. This example describes an electronic endoscope device in which multiple image sensors are mounted at the tip of an endoscope and video signals obtained by these image sensors are displayed on the same high-definition monitor. The elements and the imaging optical system are arranged so that at least a portion thereof overlaps each other, and means is provided for correcting the signal level in the overlapping portion of the imaging field of view.

[0094] This will be explained below with reference to FIGS. 36 to 38. FIG. 36 shows a distal end portion 802 of an electronic endoscope 801 equipped with a plurality of imaging elements and an imaging optical system. This figure 36
, the distal end portion 802 includes imaging optical systems 803a to 803a.
Each imaging optical system 80 is arranged with different viewing directions so that it can cover from the direct viewing direction to the side viewing direction.
CCD8 as an image sensor is on the focal plane of 3a to 803d.
04a to 804d are arranged.

As can be seen from FIG. 36, each imaging optical system 80
The fields of view 805a to 805d of 3a to 803d are arranged so as to overlap the field of view of the adjacent imaging optical system at the periphery (the overlapping portion is indicated by diagonal lines). When displayed on a display screen 806 of a high-definition monitor as shown in FIG. 37, images 807a to 807d formed by these CCDs 804a to 804d are displayed so as to overlap at the periphery (overlapping portions are indicated by diagonal lines). In this example, CCD8
04a to 804d are arranged in a zigzag pattern, but they may be arranged in a straight line.

The CCDs 804a to 804d are connected to a signal processing circuit 811 shown in FIG. 38 via cables 808 and 809. CC in signal processing circuit 811
The CCD drive signal from the D drive circuit 812 is transmitted through the cable 8
08 to each CCD 804a to 804d,
The video signals photoelectrically converted by each CCD 804a to 804d are read out, and the read video signals are transferred to the cable 809.
The corresponding CCD signal processing circuits 813a
~813d is input.

[0097] Each CCD signal processing circuit 813a to 813d
After performing various signal processing (for example, clamp, knee, γ conversion, color signal processing, white balance, AGC, etc.), the signals are converted into digital signals by A/D converters 814a to 814d, and then stored in memories 815a to 815d. are stored in each.

The video signal data stored in each memory 815a to 815d are images 807a to 807 shown in FIG.
d are read out in order according to the positional relationship of the switch means 8.
16 and added by an adder 817. The output of this adder 817 is input to an overlap detection circuit 818 and a signal level correction circuit 819.

Adjacent CCDs (for example, 804a and 804
b, 804b and 804c, etc.) captured images 807a to 80
In the overlapping part at 7d, both video signal data are read out from the memories 815a to 815d and added.
The signal level of the overlapping portion is higher than that of the non-overlapping signal level portion.

[0100] The overlapping portion detection circuit 818 detects the overlapping portion by detecting the change point, and controls the signal level correction circuit 819, so that the signal level is different between the overlapping portion and the non-overlapping portion. Correct for continuity. For example, in the overlapped portion, the gain of the signal level correction circuit 819 is controlled to 1/2 to correct discontinuity.

The output of the signal level correction circuit 819 is D
After being converted into an analog signal by the /A converter 820, the signal is input to a high-definition monitor via a signal processing circuit (not shown).

According to the fourteenth embodiment, images are taken with the surrounding areas overlapping by a plurality of imaging means, and the images obtained by these imaging means are connected and displayed on a high-definition monitor. It is possible to obtain continuous panoramic images with a wide field of view.

Next, a fifteenth embodiment of the present invention will be described. This embodiment is an electronic endoscope device in which a plurality of image sensors are mounted at the tip of an endoscope and video signals obtained from each element are displayed on the same high-definition monitor. are made common, and the common drive signal is transmitted by the same transmission means. A detailed explanation will be given below with reference to FIGS. 39 and 40.

FIG. 39 shows the distal end 8 of the electronic endoscope 801'.
02 is shown. This electronic endoscope 801' is the electronic endoscope 801 shown in FIG. 36, in which a buffer circuit 831 is provided in the distal end portion 802, and the input end of this buffer circuit 831 is connected to the main body (not shown) via a cable 832. CCD drive circuit (for example, CCD drive circuit 812 in FIG. 38)
), and the drive signal supplied from this CCD drive circuit is once input to a buffer circuit 831, and distributed by this buffer circuit 831 to each CCD 804a to 80.
4d.

As shown in FIG. 40, the configuration of the buffer circuit 831 is as shown in FIG.
D804a to 804d are distributed to drive signals, and each C
It is supplied to CDs 804a to 804d. Although FIG. 40 shows one signal line for simplicity, there are actually multiple signal lines, and each signal line has buffers 833a to 833a.
33d is provided for distribution.

Other structures and operations are the same as those of the fourteenth embodiment. According to this embodiment, CCDs 804a to 804
Since the common cable 832 is used as the transmission cable for the drive signal that drives the electronic endoscope 801
The number of cables inserted inside can be reduced. In other words, it has the advantage that the diameter of the insertion portion can be reduced.

Next, a sixteenth embodiment of the present invention will be described. This embodiment relates to a signal processing circuit provided in the main unit of an electronic endoscope shown in the 14th or 15th embodiment, and is capable of generating wide-field panoramic images with good continuity and high resolution from video signals of multiple image sensors. It is intended to be made into a statue. A detailed explanation will be given below with reference to FIG. 41.

[0108] Similar to the 14th embodiment or the 15th embodiment,
Each video signal read out from the CCDs 804a to 804d is subjected to various signal processing in CCD processing circuits 813a to 813d, and then sent to A/D converters 814a to 814d.
It is converted into a digital signal by 814d, and once stored in memory 815.
It is stored in a to 815d. Memories 815a to 815d
Each video signal data stored in is read out according to the position of the image displayed on the monitor screen, and is read out according to the position of the image displayed on the monitor screen.
are gated and input to coefficient multipliers 841a to 841d, respectively, and also to a correlation detection position correction circuit 842.

The correlation detection position correction circuit 842 detects the CCD 804a which is being read from the memories 815a to 815d.
Detecting the correlation between the overlapping portions of the imaging fields of view of ~804d,
Find the position correction value that maximizes the correlation, and store it in memory R/
It is output to the W control circuit 843 and level correction control circuit 844. The memory R/W control circuit 843 stores the corresponding video signals in the memories 815a to 815a based on the position correction value.
The timing of reading from 815d is controlled to correct the image shift in the overlapping portion of the imaging field of view.

Further, the level correction control circuit 844 controls the coefficients of the coefficient multipliers 841a to 841d based on the position correction value to correct level discontinuity in the overlapping portion of the imaging field of view. The outputs of each coefficient multiplier 841a to a841d are added by an adder 845, and then added to a D/A converter 844.
6, the signal is converted into an analog signal and output to a high-definition monitor via a signal processing circuit (not shown). This 16th
In this embodiment, as in the 14th or 15th embodiment, a wide field of view image can be obtained, and since the display position of each image is corrected, a panoramic image with good continuity and high resolution can be obtained. Can be done.

Next, a seventeenth embodiment of the present invention will be described. The purpose of this embodiment is to obtain a panoramic image with a wide field of view and higher resolution. Below, Figures 42 and 43
This will be explained in detail with reference to . An electronic endoscope system 901 according to a seventeenth embodiment shown in FIG. endoscope 90
A signal processing circuit 90 that performs signal processing for the second imaging means.
3, and a high-definition monitor (not shown) that displays the signal-processed video signal.

[0112] The distal end portion 905 of the electronic endoscope 902 includes two imaging optical systems 906a and 906b, and a CCD 907 disposed on the focal plane of each imaging optical system 906a and 906b.
It has two built-in imaging means: a and 907b. As can be seen from the illustration, there are two imaging optical systems 906a and 906b.
(CCDs 907a and 907b) are arranged so that their imaging fields of view partially overlap. As shown in FIG. 43, two CCDs 907a and 907b are arranged in an overlapping portion 908 of two CCDs 907a and 907b such that their pixel pitches P are shifted by 1/2.

The CCDs 907a and 907b are connected to cables 912a and 91 in the electronic endoscope 902 using drive signals generated by a CCD drive circuit 911 in the signal processing circuit 903.
The video signal is read out by being supplied through 2b. The two video signals are respectively input to the corresponding CCD signal processing circuits 914a and 914b via cables 913a and 913b within the electronic endoscope 902, and after various signal processing, are converted into digital signals by A/D converters 915a and 915b. The signals are converted into signals and temporarily stored in memories 916a and 916b, respectively.

Each video signal data stored in memories 916a and 916b is transmitted to both CCDs 907a and 907a shown in FIG.
07b are read out in order according to the positional relationship and input to a multiplexer (MUX) circuit 917. This MUX circuit 917 outputs the video signal as it is in the area of one CCD alone, and outputs the video signal as it is in the overlapping area 908 of the images.
Two video signals are time-division multiplexed and output. The output of this MUX circuit 917 is converted into an analog signal by a D/A converter 918, and output to a high-definition monitor via a signal processing circuit (not shown).

[0115] In this embodiment, two CCDs 907a,
The pixels 907b are arranged with a 1/2 pitch shift from each other, and time-division multiplexing is performed in the overlapping part 908 of the field of view (image), so the resolution of the image in this part 908 can be greatly improved. becomes possible.

[0116] It is also possible to construct different embodiments by partially combining each of the embodiments described above. Furthermore, the present invention can be similarly applied to an electronic endoscope that uses a TV camera that includes a plurality of image pickup devices instead of an electronic endoscope that includes a plurality of image pickup devices.

[0117]

[Effects of the Invention] As described above, according to the present invention, images from multiple image sensors are displayed simultaneously on a high-definition monitor, so they can be displayed at a higher resolution than the conventional example, improving diagnostic performance. can.

[Brief explanation of the drawing]

FIG. 1 is an explanatory diagram showing the structure of the distal end side of an electronic endoscope in a first embodiment of the present invention.

FIG. 2 is a block diagram showing a schematic configuration of the first embodiment.

FIG. 3 is an explanatory diagram showing an example of display on a monitor in the first embodiment.

FIG. 4 is a block diagram showing a schematic configuration of a second embodiment of the present invention.

FIG. 5 is an explanatory diagram showing the structure of the distal end side of the electronic endoscope in the second embodiment.

FIG. 6 is an explanatory diagram showing an example of display on a monitor in the second embodiment.

FIG. 7 is an explanatory diagram showing another example of display on the monitor in the second embodiment.

FIG. 8 is a configuration diagram of a third embodiment of the present invention.

FIG. 9 is an enlarged view of a light shielding member in a third embodiment.

FIG. 10 is a configuration diagram of a fourth embodiment of the present invention.

FIG. 11 is a front view of a rotary filter in a fourth embodiment.

FIG. 12 is an explanatory diagram of the operation of the fourth embodiment.

FIG. 13 is an explanatory diagram showing the structure of the distal end side of an electronic endoscope in a fifth embodiment of the present invention.

FIG. 14 is a front view of FIG. 13.

FIG. 15 is a sectional view taken along the line AA' in FIG. 13;

FIG. 16 is a configuration diagram of a sixth embodiment of the present invention.

FIG. 17 is an explanatory diagram of the operation of the sixth embodiment.

FIG. 18 is a schematic configuration diagram of a seventh embodiment of the present invention.

FIG. 19 is a block diagram showing the configuration of a multi-high resolution frame memory device in a seventh embodiment.

FIG. 20 is an explanatory diagram showing an example of display on a monitor in the seventh embodiment.

FIG. 21 is a schematic configuration diagram of an eighth embodiment of the present invention.

FIG. 22 is a block diagram of a multi-high resolution frame memory device in an eighth embodiment.

FIG. 23 is an explanatory diagram showing an example of display on a monitor in the eighth embodiment.

FIG. 24 is a schematic configuration diagram of a ninth embodiment of the present invention.

FIG. 25 is a block diagram of a multi-high resolution frame memory device in a ninth embodiment.

FIG. 26 is an explanatory diagram showing an example of display on a monitor in the ninth embodiment.

FIG. 27 is a schematic configuration diagram of a tenth embodiment of the present invention.

FIG. 28 is a configuration diagram of the main parts of the tenth embodiment.

FIG. 29 is an explanatory diagram showing an example of display on a monitor in the tenth embodiment.

FIG. 30 is a schematic configuration diagram of an eleventh embodiment of the present invention.

FIG. 31 is a block diagram of a multi-high resolution frame memory device in an eleventh embodiment.

FIG. 32 is an explanatory diagram showing an example of display on a monitor in the eleventh embodiment.

FIG. 33 is a schematic configuration diagram of a twelfth embodiment of the present invention.

FIG. 34 is an explanatory diagram of an example of display on a monitor in the twelfth embodiment.

FIG. 35 is an explanatory diagram showing an example of display on a monitor in a thirteenth embodiment of the present invention.

FIG. 36 is a diagram showing a distal end portion of an electronic endoscope according to a fourteenth embodiment of the present invention.

FIG. 37 is an explanatory diagram showing how images by four CCDs are displayed simultaneously on a high-definition monitor in the fourteenth embodiment.

FIG. 38 is a block diagram showing the configuration of a signal processing circuit in a fourteenth embodiment.

FIG. 39 is a diagram showing the distal end of an electronic endoscope according to a fifteenth embodiment of the present invention.

FIG. 40 is a circuit diagram of a buffer circuit in a fifteenth embodiment.

FIG. 41 is a block diagram showing the configuration of a signal processing circuit in a 16th embodiment of the present invention.

FIG. 42 is a schematic configuration diagram of a seventeenth embodiment of the present invention.

FIG. 43 is a diagram showing the positional relationship between the overlapping portions of two CCDs in the seventeenth embodiment.

[Explanation of symbols]

1...Electronic endoscope system 2...Electronic endoscope 3...Control device 4...High-definition monitor 5...Insertion section 6...Distal end portion 7a, 7b, 7c, 7d, 7e...CCD 8a, 8b, 8
c...Objective lens system 9a, 9b, 9c, 9d, 9e...Drive circuit 11a,
11b, 11c, 11d, 11e...Image memory 12...Image synthesis circuit 13...Video processing circuit

Claims (1)

[Claims] Claim 1: A plurality of image sensors arranged at the distal end of an endoscope, and video signals obtained by the plurality of image sensors are combined into one image sensor.
What is claimed is: 1. An electronic endoscope system comprising a signal processing means for simultaneously displaying images on two high-definition monitors.