JPH01297044A - Electronic endoscope device - Google Patents

Abstract

PURPOSE:To miniaturize a circuit scale and to execute an inexpensiveness by providing a solid-state image pickup element to cause at least one of characteristics on a picture element constitution into the same to at least two image pickup means among plural image pickup means. CONSTITUTION:For example, for three kinds of solid-state image pickup elements 18a, 18b and 18c provided to an endoscope, a picture element number ratio is detected by a scope discriminating circuit 26, and a control signal to indicate the picture element number ratio is outputted to a sampling pulse generating circuit 29, a memory control circuit 32 and a CCD driver. The CCD driver generates driving pulses in a number adaptive to the number of picture elements, the pulses are impressed to the solid-state image pickup elements 18, and the sampling pulse generating circuit 29 generates a sampling pulse from an electric signal read by the driving pulse. Further, the memory control circuit 32 writes a chrominance signal illuminated by respective color lights to respective frame memories 37R, 37G and 37B. Thus, the changeover of a minimum circuit constant is sufficient, the circuit scale can be miniaturized, and the inexpensiveness can be executed.

Description

DETAILED DESCRIPTION OF THE INVENTION [fl: Field of Application of Rakudo] The present invention relates to an electronic endoscopy vL wave device that can use a plurality of endoscopes.

[Problems that conventional technology and inventions are trying to solve In recent years,
Endoscopes are widely used, and can be used to observe internal organs, etc. by inserting a long and thin insertion section into a body cavity, and to perform various therapeutic procedures using a surgical incision inserted into a treatment instrument channel as needed. It is used.

Furthermore, various electronic endoscopes using solid-state imaging devices such as charge-coupled devices (CODs) have been proposed.

By the way, in conventional video cameras, the pixel size or the number of vertical and horizontal pixels (
Hereinafter, this will be referred to as pixel configuration. ) was only one type.

However, in recent years, electronic endoscopes can be used to observe a wider variety of areas, and the outer diameter allowed for the endoscope also varies depending on the observation area. In particular, endoscopes that are used to observe extremely narrow areas such as the tip of the trachea and blood vessels use relatively large solid-state image sensors, such as those used in electronic endoscopes for lower gastrointestinal tracts such as the large intestine and small intestine. Therefore, it is impossible to achieve sufficient diameter reduction. Therefore, as in the past, one type of solid Md'
fA 1'r Kodaban Pugu cannot adequately correspond to various observation areas.

Therefore, solid-state imaging elements of different sizes are used depending on the area to be observed, but in this case, the number of pixels and sensitivity of the solid-state imaging elements differ, which requires switching of circuit constants such as interpolation coefficients. Otherwise, the adjustment of the automatic gain control circuit (hereinafter not abbreviated as 8GC) becomes complicated.

In order to deal with the above problem, Japanese Patent Application Laid-Open No. 61-179129
In the publication, storage means for storing various condition information such as the type of endoscope, white balance, the number of pixels of the solid-state III image element, and the sensitivity of the solid-state 'DD image element is hidden in the endoscope main body. By connecting the connector on the mirror body side to the connector on the video wrestling section, the reading device on the bidet delta bronzer side reads the conditions, transmits the conditions to the control section, and automatically reads the conditions. A technique for performing settings has been disclosed.

However, in the prior art described in E, a large number of conditions are stored in order to be compatible with a plurality of different endoscopes, and furthermore, the circuit size is small and costs are reduced because adjustments are automatically made to match the large number of conditions. There was also the problem that it turned into a field.

[Object of the Invention] The present invention has been made in view of the above-mentioned circumstances, and by making the characteristics of the pixel configuration of a solid-state image sensor the same for two or more types of solid-state image sensors, it is possible to It is an object of the present invention to provide an electronic endoscope device that requires minimal switching of circuit constants even when using an electronic endoscope, can reduce the circuit scale, and can reduce the cost of installation.

[Means for Solving the Problems 1] The electronic endoscope apparatus of the present invention includes solid-state image sensors having at least one of the same pixel configuration characteristics in at least two of the plurality of image pickup means. I have prepared it.

[Operation] In the present invention, pixels having the same pixel size are provided in solid-state i@ elements having different numbers of pixels. The electrical signals output from these solid-state image sensing devices are adjusted with respect to the characteristics of the pixel configuration and then displayed in a patterned manner.

[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 is an explanatory diagram of the imaging surface of the solid-state image sensor, Figure 2 is a schematic diagram of the image processing circuit, and Figure 3 is an explanatory diagram of the entire electronic endoscope device.
Figure 4 is an endoscope! FIG. 5 is an explanatory diagram of the signal generation circuit of the pixel configuration detection means, and FIG. 6 is an explanatory diagram of the discrimination circuit of the pixel configuration detection means.

In FIG. 3, the electronic endoscope device 1 is used for various purposes. 12A, 2B, 2C, and this endoscope 2 (representatively U2A
, 28.2G and 1°) can be connected to the right J control unit Pj 3
and a monitor 4 that displays the video signal output from the control device 3 on a screen.

Each of the endoscopes 2 includes an elongated insertion section 6, a large-diameter operation section 7 connected to the rear end of the insertion section 6, a light guide extending from the side of the operation section 7, and a light guide. Signal cable 8
It is equipped with

At the rear end of the light guide and signal cable 8,
Light guide connector 15 and signal connector 14
are provided, and the light guide connector receiver 20 of the control device 3,! : (For No. 8) Connected to connector receiver 16.

The control device 3 is connected to the monitor 4 by a signal cable 17.

FIG. 1 shows 31! which can be connected to the control unit @3! Solid-state image sensing device 18a provided in Class I endoscopes 2A, 2B, and 2C
, 18b, 18c (representatively referred to as 18) and forming imaging surfaces 19a, 19b, 19c (representatively referred to as 19).

21b and 21G (denoted as 21 as a representative).

The size of each pixel 21 constituting the l1il image plane 19 is kl in the vertical direction, 11 . nl, and the horizontal direction is 2
．． +2. If n2, then kl=2=+1=12
=n1 =n2. Further, if the number of pixels in the vertical direction is KV, LV, and NV, and the number of pixels M in the horizontal direction is Kh, Ll+, and Nh, then KV≠1v≠NV or Kh≠Lhf−Nh.

The subject image captured by the solid-state image probe 18 is subjected to signal processing as shown in FIG.

The electrical signal photoelectrically converted by the solid-state image sensor 18 is input to the image processing means 22 . Further, the pixel configuration detecting means 23 detects the vertical and horizontal pixel number ratio of the solid-state R image element 18. This pixel configuration detection means 23 inputs a control signal indicating the ratio of the number of vertical and horizontal pixels to the video processing control means 24, and by receiving this control signal, the video processing control means 24 is adapted to the solid-state imaging probe 18. Sync 15
The number is output to the video processing means 22.

The first video processing stage 22 performs video processing on the electric signal containing video information using [the synchronous signal Y] to generate a video signal and output it to the monitor 4 .

Next, a frame-sequential video processing circuit will be specifically explained.

In FIG. 4, a light source section 9 is provided within the control device 3. As shown in FIG. The light source unit 9 includes a light source lamp 11 that generates illumination light, and a color separation filter (not shown) that chronologically separates the illumination light output from the light source lamp 11 into red, green, and blue color lights, for example. A rotating filter 12 that rotates the rotating filter 12, a motor 13 that rotationally drives the rotating filter 12, and a light guide 13a that collects the colored light that has passed through the rotating filter 12.
Shine on the incident end face! The light guide 13a includes a condenser lens 10 of 8tJ.The illumination light incident on the light guide 13a is transmitted to the endoscope 2 and illuminates the subject.

The light that illuminated the subject enters the solid-state imaging probe 18 as reflected light. The subject image formed on the imaging surface 19 of the solid-state imaging probe 18 is photoelectrically converted and sent to the image processing means 2 as an electrical signal.
2 is input. Further, the solid-state image sensor 18 is detected by the screen discrimination circuit 26 as the pixel configuration detection means 23 (the number of pixels in the vertical direction Kv).

Lv, Nv and the number of pixels in the horizontal direction Kh, Lh, Nh can be detected.

Scope discrimination circuit 26 that constitutes the pixel configuration detection means 23
A circuit for outputting a signal for discrimination is constructed as shown in FIGS. 5 and 6.

As shown in FIG. 5, the signal connector 14△ of each endoscope 2
, 148.140 is the first congratulation! Two terminals 51.51 are provided to output a signal for detecting the number of pixels at t2 (other signal terminals are omitted), and the control device 3 connects a resistor between the two terminals 51.51. The scope discrimination circuit 26 discriminates the value, and the discrimination result is output to the sampling pulse generation circuit 29.

When there are three types of endoscopes 2 as in this embodiment, the two terminals 51 and 51 of the connector 14A of the endoscope 2A are short-circuited with the conductor 52, and the connector 14 of the connector 112B of the endoscope 2A is
At B, the two terminals 51 and 51 are connected to a resistor R of, for example, 220Ω.
At the connector 14C of the endoscope 2C, the two terminals 51 and 51 are opened (opened) and equivalently connected to an infinite resistance.

On the other hand, the scope discrimination circuit 26 has input terminals 53 and 53 of the signal connector receiver 16, as shown in FIG.
3 is connected to the non-inverting input terminals of the comparators 54 and 55, and is also grounded via a resistor R of, for example, 220Ω.

On the other hand, to the inverting input terminal of the comparator 54, a voltage V1 of, for example, 3 to 4 V is applied by a reference voltage source, and to the inverting input terminal of the other comparator 55, a voltage V1 of 3 to 4 V is applied by a reference voltage source.
For example, a voltage v2 of 1 to 2v is applied. In this way, whether the 2-bit signal output from the output end 56,56 of each comparator 54,55 is within the range? l! This is a control signal output corresponding to the pixel configuration of 1t2.

In this configuration, for example, when the connector 14A of the endoscope 2A is connected, the outputs of the comparators 54 and 55, which serve as control signals, become "l HIT", and the connector 14B of the endoscope 2B is connected. then comparator 54.55
The output of the comparator 54.55 becomes L" 111 T+ when the connector 14C of the endoscope 2C is connected.

The scope discrimination circuit 26 inputs a control signal indicating the pixel number ratio as described above to the sampling pulse generation circuit 29 in the video processing control means 24, and the sampling pulse generation circuit 2
9 generates a sampling pulse. This sampling pulse generation circuit 29 receives a synchronization signal from a synchronization signal generator 31 that controls a CCD driver (not shown) that outputs a drive clock to the solid-state imaging probe 18 . This synchronizing signal generator 31 also inputs a synchronizing signal to a memory control circuit 32 which receives a control signal corresponding to the pixel number ratio of the scope discriminating circuit 26. Note that the scope discrimination circuit 26 outputs a control signal indicating the pixel number ratio to a CCD driver (not shown).

The electrical signal input to the video processing means 22 is sent to the preamplifier 2.
7 and is input to a sample hold circuit 28 which samples and bolds the sample by the sampling pulse inputted from the sampling pulse generating circuit 29.

After sample and hold, the γ correction circuit 33 performs γ correction and A
The signal is converted into a digital signal by the /D converter 34. and,
Via a multiplexer 36 which is switched by a signal from the memory control circuit 32, the signals imaged under sequential illumination of R2O and B are written into an R frame memory 37R, a G frame memory 37G and a B frame memory 37B. The signal data written in each of these frame memories 37R, 37G, and 37B are read out simultaneously, and each D/
The A converter 38 converts the color signals into ablog color signals R, G, and B.
While being output to the matrix circuit 39, the three primary colors (g
It is designed to be outputted to the monitor 4 via the buffer 42 as @RGB. In addition, the matrix circuit 39
generates the luminance signal Y and color difference signals R-Y, B-Y and outputs the NT
The signal is input to an SC encoder 41, and an NTSC composite video signal is output to the monitor 4.

The operation of the electronic endoscope device 1 configured as described above will be explained.

The pixel number ratio of the solid-state imaging probes 18a, 18b, and 18c is detected by the scope discrimination circuit 26, and a control signal indicating this pixel number ratio is output to the simplifying pulse generation circuit 29, the memory control circuit 32, and the CCD driver (not shown). do. As a result, the CCD driver generates a number of drive pulses that match the number of pixels and applies them to the solid-state imaging probe 18, and the lean-bring pulse generation circuit 29 samples and holds video components from the t-air signal read out by the drive pulses. Furthermore, the main control circuit 32 generates a sampling pulse at a timing that is possible for each frame memory 37R, 3.
Color signals illuminated by each color light are written in 7G and 37B.

As described above, in this embodiment, the vertical and horizontal sizes of the pixels 21 of each solid-state OVa cable 18 are the same, so that the gain for the pixel curvature caused by the difference in pixel increments is There is no need to perform adjustment, and signal processing of the electrical signals output from each solid-state fit image element 18 can be performed simply by making adjustments in response to changes in the number of pixels.

Furthermore, the resolutions of the solid-state imaging probes 18 can be matched.

Furthermore, if we count the individual solid-state imaging probes 18, solid b
1 of the pixels 21 forming the imaging surface 19 of the oil image probe 18
Since the size is square, the pixel pitches in the vertical and horizontal directions are the same, and the resolution for one pixel in the vertical and horizontal directions is equal. This means that the solid-state imaging probe 1
In an electronic endoscope in which the vertical direction of the subject and the vertical direction of the solid-state imaging probe 18 do not necessarily match, it is possible to equalize the vertical and horizontal resolution of the displayed image in any case. can.

Furthermore, since the pixels 21 are square, it is very suitable for performing image processing such as measuring the size of any part of a subject on a displayed image.

In this embodiment, there are three types of solid-state imaging cords 18, but the number is not limited to this, and the number may be two or four or more types.

FIG. 7 relates to a second embodiment of the present invention, in which a solid-state image element is
FIG. 3 is an explanatory diagram of a Va image plane.

This embodiment uses the solid-state imaging probes 18a and 1 described in the first embodiment.
Endoscope 2△, 2B equipped with 8b and a new solid-state imaging probe 1
This includes an endoscope 2D equipped with an 8d. The size of the pixels 21d forming the imaging surface 19d of this solid-state image sensor 18d is indicated by m1 in the vertical direction and 2nd in the horizontal direction, and the number of pixels in the vertical direction is Mh.

1≠11≠m1≠ and 2≠12≠
m2. In addition, the number of each pixel is KV + Lv + Mv
Or, Kh=7−Lh≠Ml+, and solid Ht
The number of pixels of the i-image element 18d is Mh=MV.

The video processing circuit of this embodiment will be explained with reference to FIG.

The solid-state imaging probe 18d is connected to another solid-state R-image probe 18)1.
．． 18k), the size of the pixel 21 is different, so the signal level of the electrical signal to be photoelectrically converted is different. Therefore, an automatic gain control circuit is provided within the video processing means 22 to adjust these different signal levels. This automatic gain control circuit receives from the video signal processing control means 24 a control signal corresponding to the sensitivity of the solid-state image sensor 18d detected in advance by the image configuration detection means 23, so as to obtain the optimum gain. The electrical signal whose signal level has been adjusted is processed by the video processing circuit described in the first embodiment and displayed on the screen of the monitor 4.

As described above, according to this embodiment, the solid-state image sensor 18d has a different pixel size from the other solid-state image sensors iaa and 18b, but the number of vertical and horizontal pixels is the same, so that the vertical and horizontal resolution of the displayed image is can be made equal.

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

Note that in this embodiment, the solid-state image sensor 18 is of three types, and the solid-state image sensor 18 is of two types with the same pixel 21 size, but the same solid-state image sensor 18 is It's good to have more than one type.

8 to 11 relate to a third embodiment of the present invention, in which FIG. 8 is a block diagram of an endoscope apparatus, FIG. 9 is a block diagram of the internal configuration of an image processing means and an image processing control means, 10th
The figure is a block diagram of the image enlarging section, and FIG. 11 is a block diagram of the image reducing section.

The present invention will be explained using FIGS. 1(a) and 1(b) and FIGS. 8 to 11.

In FIGS. 1(a) and (b), in this example, the solid ms
The pixel number ratio of elements 18a and 18b is Kv:Lv =Kh
: Lh, and the vertical and horizontal pixel number ratios are the same.

In FIG. 8, the electric signal converted by the solid-state Re element 18 is amplified by a preamplifier 27, converted into a digital signal, and input to the image processing means 22. Further, the number of pixels of the solid-state image sensor 18 is detected by the pixel configuration detection means 23, and a control signal indicating this number of pixels is generated and inputted to the interpolation coefficient control means 48.

The image processing means 22 is provided with an image storage means 46 composed of, for example, a plurality of line memories, and data is written into this line memory line by line. The signal data written in the image storage means 46 is read out and inputted to the image interpolation means 47, where it is enlarged and interpolated in the vertical and horizontal directions. The image interpolation means 47 has an optimum interpolation coefficient and magnification rate set by the interpolation coefficient control means 48, so that the image magnification rate and the interpolation rate are controlled.

The video signal interpolated and expanded by the image interpolation means 47 is then subjected to signal processing by the video processing circuit described in the first embodiment and displayed on the screen of the monitor 4.

In this embodiment, when Kh>Lh, the large solid-state image sensor 18a is used for observing lower digestive organs such as the large intestine and small intestine, and the small solid-state image sensor 18b is used for observing extremely narrow diameter parts such as blood vessels and bronchi. The pixel count difference can be quite large.

Therefore, if both are driven by the same driving method, there is a possibility that the image display surface of the solid-state image sensor 18b will be significantly smaller than that of the solid-state image sensor 18a. Therefore, in the film, an image storage means 46 shown in FIG. 8 and an image interpolation means 47 for interpolating the video signals of pixels of a plurality of lines from the image storage means 46 are provided in the video processing means 22, and the image processing means 22 is provided with an image storage means 46 shown in FIG. Expanding.

Although diameter reduction is the most important issue in electronic endoscopes,
Solid R image element 1 for lower digestive organs that allows a relatively large diameter
Even if it is 8 cm, the actual situation is that it is not always possible to increase the number of pixels sufficiently because the diameter must be made thinner to reduce patient pain. Therefore, in electronic endoscopes, it is necessary to more or less electronically enlarge images. If interpolation is not performed at this time, the image will be mosaic-like, so interpolation is performed as described above. If the number of pixels in the vertical and horizontal directions of 18 is uneven, the magnification ratio and the degree of interpolation must be changed independently in the vertical and horizontal directions each time the solid-state imaging element 18 is switched, which is extremely troublesome. However, according to this embodiment, since the ratio of the number of pixels in the vertical and horizontal directions of each solid-state image sensing device 18 is the same, the circuit that can enlarge and interpolate the image at the same ratio in the vertical and horizontal directions can be constructed simply and inexpensively.

The other functions and effects of Configuration 1 are the same as those of the first embodiment.
be.

In this embodiment, the pixel number ratios of one set of solid-state R image elements 18 are the same, but the ratio is not limited to this, and two or more sets may be the same. Furthermore, the vertical and horizontal pixel number ratios of three or more types of solid-state i-image elements 18 may be the same for one set.

Furthermore, the interpolation coefficient control means 48 and the video processing means 22 may be configured as shown in FIGS. 9 to 11 so that not only image enlargement but also image reduction can be performed.

In FIG. 9, the video signal obtained from the solid-state R image element 18 is input to the video processing means 22.

This input video signal is branched, and one of the signals is expanded and interpolated in the vertical or horizontal direction by a first image expansion section 58. The video signal from the first image enlarging section 58 is transmitted to the first image enlarging section 5 by a second image enlarging section 59.
The image is enlarged and interpolated in the direction perpendicular to the direction enlarged by 8. Further, the video signal to be used is reduced in the vertical or horizontal direction by the first image reduction section 61. The video signal from the first image reduction section 61 is reduced by a second image reduction section 62 in a direction perpendicular to the direction in which it was reduced by the first image reduction section 61.

Note that the first and second image enlarging sections 58 and 59 and the first and second image reducing sections 61 and 62 constitute the video processing means 22.

The first and second image enlargement sections 58 and 59 and the first and second image reduction sections 61 and 62 control the image quality by a master control 64 provided in an enlargement/reduction ratio control section 63 as the video processing control means 24. The enlargement rate, interpolation rate, and reduction rate are controlled. The master control 64 receives a pixel configuration detection signal from the scope discrimination circuit 26 that detects the pixel configuration of the solid-state imaging probe 18, and sends an enlargement/reduction rate control signal corresponding to the image configuration to the previous image enlarging unit 5.
8.59 and the image reduction unit 61.62. Furthermore, the master control 64 receives control signals manually from a display image enlargement/reduction switching means 66. This display image enlargement/reduction switching means 66 allows the size of the display image to be selected by external input means such as a button switch. Then, the display image enlargement/reduction switching signal from the display image enlargement/reduction switching means 66 is input to the master control 64. The master control G4 divides the pixel configuration detection signal from the scope discriminating circuit 26 and the display image enlargement/reduction switching signal from the display image enlargement/reduction switching means 66 to obtain an appropriate enlargement/reduction ratio. An enlargement rate control signal is output to the image enlargement units 58 and 59, or a reduction rate control signal is output to the image reduction units 61 and 62.

Next, an example of an image enlarging section, which is the first image enlarging section 58 or the second image enlarging section 59, will be explained using FIG. 10.

This horizontal image enlarger receives a digital video signal and can alternately switch between writing and reading operations.
one line memory 68,69 and the line memory 68
．． The two latches 71.72 that input the output of 69 and the output of the wrap 71.72 are each input with an interpolation coefficient αij
, βij (αij≦′1.βij≦1.aij+β1j
= 1: i, j are integers) and this lookup table 73.74
and an adder 76 that adds and outputs the output. Data is written into the line memories 68 and 69 alternately line by line, and read out in synchronization with a read clock signal from the enlargement/reduction ratio control section 63. Further, only the signals synchronized with the latch clock from the surface width expansion/reduction rate control section 63 are multiplied by N in the latches 71 and 72. The signals stored in the latches 'f-71 and 72 continue to be held until the next latch clock is sent from the enlargement/reduction ratio control section 63. Said latch 7
The output of 1.72 is multiplied by interpolation coefficients αij and β1j in lookup tables 73 and 74. The interpolation coefficients αij and βij are switched for each pixel by a coefficient switching signal from the enlargement/reduction ratio control section 63.

Also, the first image reduction unit 61 or the second image reduction unit 62
An example will be explained using FIG. 11.

The video signal for one frame obtained from the solid-state AM element 18 is accumulated in the frame memory 81, and is processed according to the readout clock outputted from the enlargement/reduction ratio control section 63 at a timing corresponding to the image reduction ratio. The number of scan lines continues to increase, and the scan lines are thinned out.

The video signal thinned out in the vertical direction by frame memory 81 is sent to latch 82 . This latch 82 reads out the video signal pixel by pixel according to the latch clock outputted from the enlargement/reduction ratio control section 63 according to the image reduction ratio.
The video signal is thinned out in the horizontal direction. The video signal thinned out in the horizontal direction by the latch 82 is time-base corrected by a time base collector (TBC) 83, and a reduced video signal is obtained.

FIG. 12 is an explanatory diagram of a decoy image plane of a solid-state image sensor according to a fourth embodiment of the present invention.

This embodiment is an example in which solid-state image sensors 86a, 86b, and 86c having the same pixel shape and area are used.

86c are different from each other in one of the pixels in the vertical or horizontal direction, but the shape and dimensions of the pixel 87 are common, and Kh + Lh or KV≠Lv, lb≠Mh or lv f:MV, Mh≠Kh or Mv≠KV.

The other configurations are the same as in the first embodiment.

In this example, the pixel 87 is in the shape of a single character, and because it has a close positional relationship with the surrounding pixels 87, the image obtained by interpolation is more faithful than the conventional rectangular pixel. . Furthermore, if this embodiment is applied to a simultaneous imaging device that uses a color mosaic filter, for example, false colors can be reduced.

Further, in this embodiment, since the shape and dimensions of the pixels 87 are the same, there is no need to adjust the gain for the sensitivity of the pixels 87 during signal processing in any solid-state image sensor 86.
Signal processing of the upper air signal output from each solid state i1 element 86 can be performed by simply making adjustments for changes in the number of pixels.

Note that the shape of the pixels of the solid-state image sensor 86 may be other shapes, such as a circle or a hexagon.

FIG. 13 and FIG. 14 relate to the fifth embodiment of the present invention,
FIG. 13 is an explanatory diagram showing the arrangement of complementary color separation filters, and FIG. 14 is a block diagram showing the configuration of the endoscope apparatus.

In this embodiment, a color separation filter 9 is provided in front of a solid-state imaging probe 91.
The present invention is applied to a simultaneous electronic endoscope 93 equipped with 2.

The endoscope 93 is provided with an objective lens system 96 for imaging at the distal end side of an elongated insertion portion 94. A solid-state image sensor 91 driven by a drive circuit 97 is mounted on the focal plane of the objective lens system 96. is installed.

A light guide 98 formed of a flexible fiber bundle is inserted into the insertion portion 94 as an illumination light transmission means. This light guide 98 extends from the endoscope 1t93 and is connected to a light source section 99. This light source section 9
9 converts white light from a light source lamp 101 into a condenser lens 10
2 and illuminates the incident end surface of the light guide 98.
1. Illumination light C from the surface width light source section 99 passes through the light guide 98 and is emitted from the light guide 98.
Q'l is emitted from the output end face of the light beam and passes through the light distribution lens system 103 to illuminate the subject.

The reflected light from the subject reaches the solid-state image sensor 91 through an objective lens system 96, and forms an optical image. The output signal of the solid-state image sensor 91 is sent to the signal processing unit 1
It is amplified by preamplifier 106 in 04, 1-pass filter (LPF) 107°
PF) 109. When the readout frequency of the solid-state image sensor 91 is 7.16 MHz, the LPF 107,
108 passbands are 3MH2, 0, 5MH2r respectively
Yes, the center frequency of BPF109 is 3', 58MHz
, the bandwidth is approximately IMHz. Since the color arrangement of the color separation filter 92 is as shown in FIG. 13, (Cy + Ye ) ±(M(] +G) = (B+
A luminance signal of the component G+RtG)+(R+B+G)=2R+3G+2B is obtained. Wideband luminance signal Y11 and narrowband luminance signal YL are output from LPF107 and 108, respectively.
is obtained. The wideband luminance signal YH output from the LPF 107 is input to the composite video signal circuit 111. In addition, the output of the BPF 109 is transmitted to the demodulation circuit 112 and the LPF 113.
The signal is input to the addition/subtraction circuit 114 via. Demodulation circuit 11
In No. 2, the outputs of the even columns subtract the outputs of the dominant columns and alternately output the following color difference signals. Here, as a color difference signal, for one line, which is represented as n line in Fig. 13, (CM + M (] ) - (Ye + G) = (B -G signal is obtained and on the other line, denoted as n+1 line (
Ye +M(] )-(Cy 1G)=(R+G-+-
R+B)-(B+-G+G)=2R-G signals are obtained. 2B-G and 2R-G obtained here (
No. 8 is equivalent to BY and RY, respectively.

Note that the narrowband U degree signal YL output from the LPF 108
is also input to the addition/subtraction circuit 114. The color difference (No. 8 is the R-Y, B-Y signal) necessary to obtain the composite video signal, so the addition/subtraction circuit 114 uses the color difference signal and the narrowband luminance IH signal Y.
Multiply L by an appropriate coefficient and sieve these to obtain a color difference signal R
-Y.

Output B, -Y. Here, since the demodulation circuit 112 alternately outputs the color difference signals 2R-G and 2B-G for each line, the addition/subtraction circuit 114 also outputs the color difference signals R-Y and B-Y alternately for each line. Output. Therefore, the output signal of the adder/subtractor circuit 114 is synchronized by 1H (one horizontal scanning period) using the delay circuit 116 and the line switching circuit 117. That is, the color difference signal of each line is delayed by 11" period, and the color difference signal of the next line is delayed by 11" period. Line switching circuit 1 along with color difference signal
It is output from 17. The color difference signals R-Y and B-Y output from the line switching circuit 117 are modulated (3,58MHz) by a modulation circuit 118 to generate a color subcarrier signal, and this color subcarrier signal is sent to the composite video signal circuit. 111. The composite video signal circuit 111 receives this color subcarrier signal and the wideband luminance signal Y output from the LPF 107.
A composite video signal is generated based on the synchronization signal and the synchronization signal.

The demodulation circuit 112 and the addition/subtraction circuit 114 are connected to a solid-state vi provided at 1 ft 93 from the video signal processing control means 24.
A timing signal suitable for the image element 91 is inputted,
The composite video signal circuit 111 receives a synchronization signal from the video signal control means 24. The demodulation circuit 112 performs a reduction based on this timing signal and outputs a color difference signal, and the addition/subtraction circuit 11A uses this timing signal to output the color difference signal and the narrowband luminance a (ci@YL). .

Further, the video signal control means 24 receives an information signal regarding the pixel configuration of the solid-state image sensor 91 installed in the endoscope v193 from the scope discrimination circuit 26 described in the first embodiment, The timing signal and the synchronization signal suitable for the pixel configuration are output.Furthermore, the scope discrimination circuit 26 has a resistance value indicating the pixel configuration of the solid-state image sensor 91 provided in the internal camera 1193. A resistor R is connected, and the pixel configuration is determined based on this resistance value.

In this embodiment, the present invention is applied to a simultaneous imaging type endoscope, and by configuring as described above, the first
Effects similar to those of the embodiment can be obtained.

15 to 17 relate to the sixth embodiment of the present invention,
Fig. 15 is an explanatory diagram of an endoscope device in which an external TV camera is attached to an optical endoscope, Fig. 16 is an explanatory diagram of the pixel configuration detection means of the external TV camera, and Fig. 17 is an explanatory diagram of another external TV camera. FIG. 3 is an explanatory diagram of a pixel configuration detection means of a TV camera.

In this embodiment, the present invention is applied to an external TV camera attached to an optical endoscope.

In FIG. 15, the operating section 122 of the optical endoscope 121
An external TV camera 124 is removably attached to the eyepiece section 123 provided at the rear end, for example, on the right side of the solid-state image sensor 18a having the pixel configuration described in the first embodiment. This external TV camera 124 is connected to a camera control unit 127 via a signal cable 126 extending from the rear end. In addition, a flexible universal cable 128 extends from the side of the operation unit 122.
It is designed to be connected to a light source device 129.

The illumination light output from the light source device 129 is transmitted through the light guide 131 inserted through the universal cable 128, and is emitted from the distal end of the optical endoscope 121 to illuminate the subject. The return light from the subject is image guide 1.
32 and transmits the subject image to the eyepiece section 123.

This subject image is formed by an imaging lens at 0.degree. The formed optical image is photoelectrically converted and input to the signal processing circuit 134 as an electrical signal. Signal processing circuit 13
The image signal generated by 4 is transmitted through the signal cable 126.
The signal is sent to the camera control unit 127 through a plurality of signal lines 136 inserted therein. Note that a plurality of power supply wires (not shown) that can supply power from the camera control unit side to the external TV camera 124 are also inserted into the signal cable 126.

The camera control unit 127t- converts the image signal into, for example, an NTSC composite video signal, and converts the image signal into an NTSC composite video signal.
The C composite video signal is output to the TV monitor 137, and the subject image is displayed on the screen.

By the way, the signal cable 12 for the external TV camera 124
6, and the camera control unit 12
7 is provided with a resistor R1 that generates a signal indicating the pixel configuration of the solid-state image sensor 18a of the external TV camera 124.

In FIG. 16, the connector 138 of the external TV camera 124 has a pin 139 connected to both ends of the resistor R1.
．． 139 is provided protruding from the rear.

When the connector 138 and the camera control unit 127 are connected, the bin 139 is connected to the camera control unit 127.
It can be electrically connected to. Bottle holder 14
1.141 is the scope discrimination circuit 2 described in the first embodiment.
A camera discrimination circuit 149 having a configuration similar to that of 6 is connected to the camera discriminating circuit 149 to discriminate the pixel configuration of the solid-state image sensor 18a provided in the external TV camera 124.

The pixel configuration detection signal output from the camera discrimination circuit 149 is transmitted to the first
The signal is input to the video processing control means 24 described in the embodiment. The video processing control means 24 uses the pixel configuration detection signal from the camera discrimination circuit 149 to control the image enlarging section 58 .
59, image reduction units 61 and 62, and the like.

Note that the pixel configuration detection means 23 may be configured as shown in FIG. 17.

In the figure, a bin 143 is provided protruding from the rear end surface of the connector 138 of the first external TV camera 124a.

Also, the connector 13 of the second external TV camera 124b
No bin 143 is provided at the rear end of the 8. In the control unit 127 to which the connector 138 is connectably connected, a switch piece 146 constituting a switch 144 is urged toward the connector by a spring 147. When the connector 138 is connected to the camera control unit 127, this switch piece 146 is pressed by the bottle 143 and connects the contacts 148 and 148 against the force of the coil spring 147 (=J force). The contacts 148, 148 are connected to a camera discrimination circuit 149, and this camera discrimination circuit 149 is connected to the switch 14.
4 is in the closed state, the first external TV camera 124
The connection of a is detected. In addition, when the second external TV camera 124b is connected, the switch piece 146 is not pressed, the switch 144 remains open, and the camera discrimination circuit 149 is connected to the second external TV camera 124b. The connection is now detected.

The camera discrimination circuit 149 stores in advance the pixel configurations of the solid-state image sensors provided with the first external TV camera 124a and the second external TV camera 124b, and which external TV camera is connected. Depending on whether the pixel configuration is detected or not, a pixel configuration detection signal is output.

In addition, in Fig. 17, there is only one pin 143, and it is designed to detect two types of external TV cameras, but pin 1
By providing a plurality of 43, the number of external TV cameras that can detect C, that is, the number of pixel components that can detect C, may be increased.

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

[Effects of the Invention] As explained above, according to the present invention, by making the characteristics of the pixel configuration of the solid-state imaging device the same for two or more types of solid-state imaging devices, it is possible to use electronic endoscopes with different solid-state imaging devices. By using this method, only a minimum number of circuit constants need to be changed, the circuit scale can be reduced, and 11 circuits = 1 stroke can be made at low cost.

[Brief explanation of the drawing]

Figures 1 to 6 relate to the first embodiment of the present invention.
The figure is an explanatory diagram of the imaging surface of the solid-state image sensor, Figure 2 is a schematic diagram of the video processing circuit, Figure 3 is an explanatory diagram of the entire electronic VT equipment, Figure 4 is a block diagram of the endoscope equipment, FIG. 5 is an explanatory diagram of the signal generation circuit of the pixel configuration detection means, FIG. 6 is an explanatory diagram of the discriminating circuit of the pixel configuration detection means, and FIG. 7 is related to the second embodiment of the present invention. Explanatory diagram of the surface, No. 8
11 to 11 relate to a third embodiment of the present invention, FIG. 8 is a block diagram of an endoscope apparatus, FIG. 9 is a block diagram of the internal groove of the image processing means and the image processing control means, and FIG. 11 is a block diagram of the image enlargement section, FIG. 11 is an 11-dimensional diagram of the image reduction section, FIG. 12 is an explanatory diagram of the imaging surface of the solid-state image sensor, and FIG. 13 and FIG. FIG. 14 relates to a fifth embodiment of the present invention, FIG. 13 is an explanatory diagram of an arrangement of complementary color separation filters, FIG. 14 is a block diagram showing the configuration of an endoscope device, and FIGS. FIG. 17 relates to the sixth embodiment of the present invention, FIG.
The figure is an explanatory diagram of the pixel configuration detection means of an external TV camera, and FIG. 17 is an explanatory diagram of the pixel configuration detection means of another external TV camera. 18a, 18b, 1Bc--Solid 11ii (*
Elements 19a, 19b, 19cm'a Image plane 21 a, 21 b, 21 c--Pixels Figure 1 (o) (b) (C) h/18c Solid state 11 Image element 1 43 Figure 5 (a) (b) (c)
No. 6331...26 No. 7 rIA (a) (b) Old o
18b (C) h No. 8rlA Fig. 1o Fig. 11 Fig. 12 (a) h 11113 Fig. A field 87r-root (b) h Fig. 12 (C) h No. 15E! ! 16th! Il Figure 17

Claims (1)

[Scope of Claims] A plurality of different imaging means using solid-state imaging devices, a signal processing means for processing electrical signals obtained by the imaging means to generate a video signal, and displaying the video signal as an image. An electronic endoscope apparatus comprising an image display means, wherein at least one characteristic of the pixel configuration of solid-state image sensors provided in at least two of the plurality of image pickup means is the same. An electronic endoscope device featuring: