JP3337489B2 - Imaging system - Google Patents

Description

DETAILED DESCRIPTION OF THE INVENTION

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to an imaging system capable of displaying at least an optical observation image and an X-ray fluoroscopic image.

[0002]

2. Description of the Related Art Conventionally, in order to confirm the position of an endoscope insertion portion at the time of diagnosis with an endoscope, a subject to be examined is irradiated with X-rays to obtain a fluoroscopic image, and the X-ray fluoroscopic image is obtained. The endoscopic observation image is diagnosed while being displayed.

In the case of displaying such an endoscopic observation image and an X-ray fluoroscopic image, conventionally, an endoscopic observation image is taken and displayed on a monitor for the endoscope image, and the X-ray apparatus is used. X
A fluoroscopic image is obtained and displayed on a monitor for an X-ray image, and diagnosis of the endoscopic image and confirmation of the position of the endoscope insertion portion by the X-ray fluoroscopic image are performed.

However, when the endoscope observation image and the X-ray fluoroscopic image are displayed on separate monitors as described above, operation of the endoscope is performed while alternately comparing the two monitors.
Since diagnosis must be performed, operability is poor and there is a problem that operator fatigue is increased.

In order to solve the above-mentioned problem, a device capable of displaying an endoscope observation image and an X-ray fluoroscopic image on the same monitor as disclosed in Japanese Patent Application Laid-Open No. 2-68027 has been proposed. Have been. By displaying the endoscopic observation image and the X-ray fluoroscopic image on the same monitor or recording them on the same recording medium as in this device, the operability at the time of diagnosis, the accuracy and efficiency of image diagnosis are improved. Can be improved.

[0006]

SUMMARY OF THE INVENTION In an apparatus for displaying an endoscopic observation image and an X-ray fluoroscopic image, an image obtained by a frame sequential endoscope apparatus and an X-ray fluoroscopic image are displayed on the same monitor. Detects the filter position of a rotary filter for obtaining field-sequential illumination light with an encoder or the like, controls writing and reading timing of an image memory according to the filter position detected by a memory controller, and generates an image. I was

However, when an X-ray apparatus irradiates an X-ray to obtain an X-ray fluoroscopic image when generating an optical observation image by capturing an optical image of a portion to be inspected, the above-mentioned image signal May be mixed with X-ray irradiation noise.

The present invention has been made in view of these circumstances, and when an object to be inspected is imaged by an optical image imaging means, X-ray irradiation and X-ray irradiation noise are mixed into an image signal. It is an object of the present invention to provide an imaging system capable of obtaining an image of a test site with less noise by suppressing the mixed noise component even if there is any.

In order to achieve the above object, an image pickup apparatus according to the present invention is provided.
The system emits X-rays from a predetermined X-ray irradiator
Optical image capture provided in an endoscope for observing a predetermined test site
Optical image pickup signal for inputting an optical image pickup signal from the image means
X-rays are emitted from input means and an X-ray irradiator,
X-ray imaging from X-ray imaging means for imaging a fluoroscopic image of a part
X-ray imaging signal input means for inputting an image signal, and the optical image
Optical image imaging signal from imaging signal input means and X-ray imaging
Combining with the X-ray imaging signal input from the signal input means
Signal combining means for outputting a predetermined combined imaging signal;
Inputting a combined imaging signal from the signal combining means
First input / output circuit means for outputting an output characteristic, and the signal
Receiving a combined imaging signal from the combining means,
A second output for suppressing the output of a signal having a lower level than the characteristic
Second input / output circuit means for outputting the characteristic signal;
Output from the output circuit means or the second input / output circuit means.
The optical image and the X-ray based on the synthesized imaging signal
A video signal processor that generates a composite video signal by combining a perspective image
Logic circuit, and the signal combining means signal from the signal combining means.
Signal is being emitted from the X-ray irradiator.
Outputs to the first input / output circuit means,
When X-rays are not being emitted from the X-ray irradiator,
Output switching means for outputting to the second input / output circuit means;
It is characterized by having.

[0010]

[0011]

Embodiments of the present invention will be described below with reference to the drawings. 1 to 6 relate to a first embodiment of the present invention, FIG. 1 is a block diagram showing a configuration of an endoscope / X-ray observation device, and FIG. FIG. 3 is an explanatory diagram showing a configuration, FIG. 3 is a circuit diagram showing a configuration of a noise reduction circuit, and FIG.
5 is a characteristic diagram showing characteristics of the noise reduction circuit of FIG. 3, FIG. 5 is a block diagram showing a configuration of a modification of the noise reduction circuit, and FIG. 6 is an explanatory diagram showing a display screen of an observation monitor.

As shown in FIG. 2, an endoscope / X-ray observation apparatus includes an endoscope 1 inserted into a subject, an X-ray irradiator 2 for irradiating the subject with X-rays, An X-ray apparatus 3 that captures an X-ray fluoroscopic image. Endoscope 1 and X-ray device 3
Is connected to the image synthesizing unit 4, where the endoscopic observation image and the X-ray fluoroscopic image are synthesized and output to the observation monitor 5. The image synthesizing unit 4 includes a video signal processing circuit 6 that processes a signal of a subject image captured by the endoscope 1 and a scanning line conversion circuit that converts a scanning line of an X-ray fluoroscopic image obtained by the X-ray device 3. And an image synthesizing circuit 8 for synthesizing an X-ray fluoroscopic image whose scanning lines have been converted by the scanning line converting circuit 7 and an endoscopic observation image output from the video signal processing circuit 6.
And

An endoscope image control device 10 including the image synthesizing section 4 is configured as shown in FIG. Note that the endoscope image control device 10 is configured to obtain an endoscope observation image in a simultaneous manner.

In FIG. 1, an objective lens system 18 and a light distribution lens system 19 are provided at a distal end portion 13 of the endoscope 1. A solid-state imaging device 21 is provided behind the objective lens system 19, and a portion to be inspected 2 is provided on an imaging surface of the solid-state imaging device 21.
The two images are formed. Solid-state imaging device 21
Is a CCD of the endoscope image controller 10 via a signal line 23.
The driver 24 and the color separation circuit 26 are connected.

Behind the light distribution lens system 19, a light guide 2 formed of a fiber bundle for transmitting illumination light
7 are provided. The light guide 27 is inserted through the insertion portion of the endoscope 1 and the endoscope image control device 10
At the light source unit 28 provided at the first position.
The operation unit of the endoscope 1 has a scope switch 29a,
29b, 29c and 29d are provided.

The endoscope image control device 10 includes a light source 28
And a signal processing unit 31 and a control unit 32.
The light source unit 28 includes a light source lamp 3 for generating white illumination light.
3 and a condenser lens 34 for condensing the illumination light and irradiating the incident end face of the light guide 27 with the illumination light. The white illumination light from the light source 28 is transmitted through the light guide 27 and distributed. The light is emitted from the optical lens system 19 and illuminates the test site 22.

A color separation circuit 26 constituting the signal processing section 31 separates a luminance signal Y and color difference signals RY and BY from an image signal input from the solid-state image pickup device 21, and varies the luminance signal Y. Gain amplifiers 36R and 36B and A / D converter 3
7, the color difference signal RY is output to the adder 38, and the color difference signal BY is output to the adder 39. The variable gain amplifier 36R outputs the luminance signal YR ′, the gain of which has been adjusted by the control signal from the white balance control circuit 41, to the adder 38, and the variable gain amplifier 36B
Similarly, the luminance signal YB ′ whose gain has been adjusted by the control signal from the white balance control circuit 41 is output to the adder 39. The adder 38
Adds the luminance signal YR ′ to the color difference signal RY to convert the color difference signal RY ′ into the white balance control circuit 41.
And the A / D converter 37, and the adder 39 adds the luminance signal YB 'to the chrominance signal BY to add the chrominance signal BY.
'To the white balance control circuit 41 and the A / D converter 37.

The A / D converter 37 converts the input signal into a digital signal and outputs it to the image memory 42. The signal once stored in the image memory 42 is input to the image synthesizing circuit 8. On the other hand, an X-ray fluoroscopic image signal from the X-ray apparatus 3 is input to a scanning line conversion circuit 7, and the scanning line conversion circuit 7 converts a scanning line so as to conform to the image signal of the endoscope. 8 is input.

The image synthesizing circuit 8 synthesizes the endoscopic image signal from the image memory 42 and the X-ray image signal whose scanning line has been converted by the scanning line converting circuit 7 and outputs the synthesized signal to the D / A converter 43. The synthesized image signal is converted into an analog signal by the D / A converter 43 and input to the noise reduction circuit 12. The noise reduction circuit 12 suppresses a noise component of the input signal and outputs it to the video signal processing circuit 44. The video signal processing circuit 44 converts the image signal into a standard video signal (for example, an NTSC video signal). , To the changeover switch 46.

Here, the noise reduction circuit 12 is shown in FIG.
This will be described with reference to FIG. The noise reduction circuit 12 is constituted by a coring circuit.

The input signal passes through the resistor r1 and is input to the emitter follower type transistor Q1 and is also applied to the base of the transistor Q2 via the capacitor C1. The base of the transistor Q2 is grounded via a resistor r2, the emitter is connected to a negative power supply terminal -Vcc via resistors r3 and r4, and the transistor Q3 which forms a pair via a capacitor C2 and a resistor r5. Connected to emitter. The base of this transistor Q3 is a resistor r
6 and a capacitor C3 are grounded through a parallel circuit, the collector is connected to the positive power supply terminal Vcc, and the emitter is a resistor r.
7 is connected to a connection point of the resistors r3 and r4.
The collector of the transistor Q1 is connected to the positive power supply terminal Vcc, and the emitter is connected to the negative power supply terminal -Vcc via the resistor r8 and to the output terminal.

In the noise reduction circuit 12 composed of the coring circuit, when the transistor Q3 is turned on, the potential at the connection point of the emitter-side resistors r4 and r7 is applied via the resistor r3. By setting the level slightly lower, when the input signal becomes higher than this level (+ the forward voltage between the base and the emitter of the transistor Q2), the transistor Q2 is turned on, and the input to be applied to the base of the transistor Q1 is turned on. The signal is resistance r1, r3, r4, transistor Q
2 is divided by the equivalent collector-emitter resistance. By the current flowing when the transistor Q2 is turned on, FIG.
As shown on the lower side, the input / output characteristics (coring curve) change, so that the increase in the signal level of the input signal can be offset in the low-level signal range. Also,
A changeover switch 61 is provided, and when the changeover switch 61 is turned on / off by an X-ray ON signal from the X-ray device 3, when an X-ray ON signal is not input as shown in FIG. 4 (when X-rays are not irradiated). Has a linear input / output characteristic, and when an X-ray ON signal is input (at the time of X-ray irradiation), a coring curve can be changed so as to suppress a low-level signal range. Note that resistors r1, r3,
The input / output characteristics of the circuit can be varied by the values of r4, r5, and r7.

As described above, by passing the noise through the noise reduction circuit 12 having an input / output characteristic for suppressing the low-level signal range, the noise component normally distributed in the low-level range can be suppressed. It is possible to obtain a good image with less image quality. Here, the transistor Q
By interposing a series circuit of a capacitor C2 and a resistor r5 between the emitters of Q2 and Q3, the damping of a high-frequency signal such as noise is increased to increase the noise suppression effect.

Further, as shown in FIG. 5, a circuit for digitally canceling noise can be used as the noise reduction circuit 12. Digital noise reduction circuit 12a
Is composed of a recursive filter. When the digital noise reduction circuit 12a is used, the noise reduction circuit 12a is provided in a stage preceding the D / A converter 43.

The difference between the input signal and the signal of the previous frame stored in the frame memory 63 is calculated by the subtraction circuit 62, and the coefficients k and 1-k of the coefficient circuits 64 and 65 (where, 0 ≦ k ≦ 1) is set.
The input signal is multiplied by k in a coefficient circuit 64, while the output signal of the frame memory 63 is multiplied by (1-k) in a coefficient circuit 65, and both of them are added by an adding circuit 66 to remove noise components. The signal is output as a signal and is stored in the frame memory 63.

As described above, by using the digital noise reduction circuit 12a, the noise component can be suppressed as in the case of the analog coring circuit, and a good image with less noise can be obtained.

The output signal of the video signal processing circuit 44 is input to the monitor 5 and the external video recording device 11 via the changeover switch 46, and the synthesized endoscope observation image and X-ray fluoroscopic image are displayed on the monitor 5. It is supposed to be. The synthesized observation image can be recorded by the external video recording device 11. By switching the changeover switch 46, an image recorded in the external video recording device 11 can be displayed on the monitor 5.

The white balance control circuit 41 is controlled by a microcomputer 47 constituting the control unit 32.

The microcomputer 47 has a CPU 4
8 and a keyboard / panel interface circuit 51
, An external recording device interface circuit 52, an internal interface circuit 56, and a character signal generation circuit 57.

The CPU 48 includes the keyboard / panel interface circuit 51, an external recording device interface circuit 52, an internal interface circuit 56,
The operation of the character signal generating circuit 57 is controlled. The keyboard / panel interface circuit 51 interfaces with the keyboard 9 and the panel device 49 for performing various operations and instructions. The video recording device 11 is controlled.

The internal interface circuit 56 is connected to the white balance control circuit 41, the memory controller 53, the color bar / 50% white generating circuit 54 for generating a 50% white signal, and the video signal processing circuit 44. And controls these circuits. The character signal generating circuit 57 generates a character signal, outputs the character signal to the video signal processing circuit 44, and superimposes it on the subject video signal.

The memory controller 53 controls the A / D converter 37, the image memory 42, and the D / A converter 43, and includes a color bar / 50% white generation circuit 54.
Is connected to the video signal processing circuit 44. The changeover switch 46 is controlled to be switched through an internal interface circuit 56.

Next, the operation of this embodiment will be described. The white illumination light emitted from the light source lamp 33 of the light source unit 28 is condensed by the condenser lens 34 on the incident end face of the light guide 27 provided inside the endoscope 1, transmitted and transmitted from the light distribution lens system 19. The test site 22 is illuminated. The light reflected from the test site 22 is imaged on the imaging surface of the solid-state imaging device 21 by the objective lens system 18. The solid-state imaging device 21 is a solid-state imaging device called a single-chip color chip provided with a color filter (not shown) on an imaging surface. The solid-state imaging device 21 is driven by a drive signal from the CCD driver 24, converts the formed optical image into an electric signal, and outputs the electric signal. The signal output from the solid-state imaging device 21 is converted into a luminance signal Y and two color difference signals RY, B by a color separation circuit 26.
−Y, two variable gain amplifiers 36R and 36B
After the white balance is adjusted by a white balance adjustment circuit including a white balance control circuit 41, the signal is converted into a digital signal by an A / D converter 37 and stored in an image memory 42. The signal read from the image memory 42 is used for image synthesis. Input to the circuit 8.

On the other hand, the X-ray fluoroscopic image signal obtained by the X-ray apparatus 3 is inputted to a scanning line conversion circuit 7 which converts the scanning lines so as to conform to the image signal of the endoscope. Is done. Here, if the video signal processing circuit 44 and the observation monitor 5 comply with, for example, the NTSC system, the scanning lines are converted so as to conform to the NTSC system. An X-ray imaging apparatus generally uses a high-resolution monitor having 1000 or more scanning lines. Therefore, when the X-ray fluoroscopic image signal has a high resolution of, for example, 1000 or more scanning lines, a thinning process is performed by the scanning line conversion circuit 7 and scanning is performed so as to conform to the NTSC scanning line number (525). Convert the number of lines,
It is input to the image synthesis circuit 8. The video signal processing circuit 4
4 and observation monitor 5 are PAL system (625 scanning lines)
If it complies with the above, the number of scanning lines is converted to conform to this.

The image synthesizing circuit 8 synthesizes the endoscope image signal from the image memory 42 and the X-ray image signal whose scanning line has been converted by the scanning line converting circuit 7, and the synthesized image signal is D.
The signal is converted back to an analog signal by the / A converter 43 and input to the noise reduction circuit 12. In the noise reduction circuit 12,
The coring curve is switched as shown in FIG. 4 by the ON signal from the X-ray device 3 to suppress noise components distributed in a low-level range during X-ray irradiation, and output to the video signal processing circuit 44. The output signal of the noise reduction circuit 12 is converted into a standard video signal by the video signal processing circuit 44 and input to the monitor 5 via the changeover switch 46.
As shown in FIG. 6, an endoscopic observation image 58 and an X-ray fluoroscopic image 59 are displayed on the observation monitor 5.

As described above, by converting and synthesizing the scanning lines of the X-ray fluoroscopic image signal so as to match the endoscopic image signal, the endoscopic observation image and the X-ray fluoroscopic image can be converted to the same monitor. Can be displayed. Also, an image synthesized by the image recording device can be recorded. At this time, since the endoscope observation image is obtained by the simultaneous method, it is not possible to control the writing and reading timing of the image memory according to the filter position of the rotation filter of the light source by the memory controller to generate the image. Since this is not performed, the configuration is such that a rotary filter, an encoder for detecting the position, and the like are not provided, and noise does not mix into these output lines and the like, and the memory controller does not malfunction. Therefore, malfunction of the circuit due to X-ray irradiation noise during X-ray irradiation can be prevented, and an endoscope observation image and an X-ray fluoroscopic image can always be obtained stably.

FIG. 7 shows an endoscope according to a second embodiment of the present invention.
FIG. 2 is a block diagram illustrating a configuration of an X-ray observation device.

In the endoscope / X-ray observation apparatus of the second embodiment,
An image composition section 71 is provided with an aspect ratio conversion circuit 72. Video signal processing device 6 for generating an endoscopic observation image
When the monitor 5 for observation or the monitor conforms to the NTSC system, the aspect ratio of the screen is 4: 3. On the other hand, a monitor having an aspect ratio of 1: 1 may be used in the X-ray imaging apparatus. At this time, the aspect ratio of the fluoroscopic image obtained by the X-ray imaging device is 1: 1. In this embodiment,
The X from the X-ray device 3 is output by the aspect ratio conversion circuit 72.
The aspect ratio of the fluoroscopic image is converted from 1: 1 to 4: 3, and the endoscopic observation image and the X-ray fluoroscopic image are combined into an image synthesizing circuit 8.
To compose.

The X-ray fluoroscopic image obtained by the X-ray apparatus 3 is scanned by the scanning line conversion circuit 7 in the same manner as in the first embodiment.
The scanning lines are converted so as to conform to the TSC system, and the aspect ratio is converted by the aspect ratio conversion circuit 72 to 4: 4.
3 and input to the image synthesis circuit 8. The image synthesizing circuit 8 synthesizes an endoscope observation image captured by the endoscope 1 and signal-processed by the video signal processing circuit 6 and an X-ray fluoroscopic image output from the aspect ratio conversion circuit 72 to provide an observation monitor. 5, the endoscope observation image and the X-ray fluoroscopic image are displayed on the observation monitor 5.

As described above, by converting the scanning line of the X-ray fluoroscopic image signal and the aspect ratio so as to be compatible with the endoscopic image signal and synthesizing the same, the endoscopic observation image and the X-ray fluoroscopic image are made identical. Can be displayed on a monitor.

Other structures, operations and effects are the same as those of the first embodiment.

FIG. 8 shows an endoscope according to a third embodiment of the present invention.
FIG. 2 is a block diagram illustrating a configuration of an X-ray observation device.

In the endoscope / X-ray observation apparatus according to the third embodiment, the image synthesizing section 81 is provided with the scanning line conversion circuit 7 and the aspect ratio conversion circuit 72 on the output side of the video signal processing circuit 6, and the aspect ratio conversion is performed. The output of the circuit 72 and the output of the X-ray device 3 are input to the image synthesizing circuit 8.

When a high quality monitor for X-rays is used as the monitor 5 for observation, the scanning line conversion circuit 7 is used so that the endoscope image signal output from the video signal processing circuit 6 matches the X-ray fluoroscopic image signal. And the aspect ratio is converted by the aspect ratio conversion circuit 72, and the endoscope observation image and the X-ray fluoroscopic image are synthesized by the image synthesis circuit 8. At this time, the endoscope image signal is subjected to interpolation processing by the scanning line conversion circuit 7 and the number of scanning lines is 10
And the aspect ratio conversion circuit 72
To convert the aspect ratio to 1: 1 and input it to the image composition circuit 8. That is, the endoscope observation image captured by the endoscope 1 and signal-processed by the video signal processing circuit 6 is converted into one scanning line by the scanning line conversion circuit 7 and the aspect ratio conversion circuit 72.
More than 000 lines are converted to an aspect ratio of 1: 1 and are combined by the image combining circuit 8 with the X-ray fluoroscopic image obtained by the X-ray apparatus 3. Then, the synthesized image is displayed on the observation monitor 5.
And an endoscopic observation image and an X-ray fluoroscopic image are displayed on the monitor screen.

As described above, when a high-quality monitor for X-rays is used as the observation monitor, the scanning lines of the endoscope image signal and the aspect ratio are converted and combined so as to be compatible with the X-ray fluoroscopic image signal. By doing so, the endoscopic observation image and the X-ray fluoroscopic image can be displayed on the same monitor.

Other structures, operations and effects are the same as those of the first embodiment.

The number of scanning lines is 112 as an observation monitor.
Similarly, in the case of using an HDTV monitor having five lines and an aspect ratio of 16: 9, the endoscope image signal is interpolated, the scanning line and the aspect ratio are converted and synthesized, and the endoscope observation image is displayed on the HDTV monitor. And an X-ray fluoroscopic image can be displayed.

FIG. 9 is a block diagram showing an image synthesizing unit according to a fourth embodiment of the present invention and a monitor connected thereto.

In the fourth embodiment, the endoscope image control device 10
A switching circuit 91, a scanning line conversion circuit 92 for NTSC and a scanning line conversion circuit 93 for high image quality monitor are provided therein, and the number of scanning lines is converted according to the monitor to be connected. An X-ray fluoroscopic image is synthesized.

When the monitor to be connected is the NTSC monitor 94, the switching circuit 91 selects the NTSC scanning line conversion circuit 92, converts the number of scanning lines to 525 so as to conform to the NTSC system, and converts the image. The images are synthesized and output to the NTSC monitor 94. If the aspect ratio needs to be converted, it is converted to 4: 3. When a monitor of the PAL system is connected, a scanning line conversion circuit for converting the number of the scanning lines into 625 and the aspect ratio of 4: 3 is used so as to be compatible with the PAL system.

On the other hand, the monitor to be connected is a high image quality monitor 9
If it is 5, the switching circuit 91 selects the high image quality monitor scanning line conversion circuit 93, converts the number of scanning lines to 1000, synthesizes an image, and outputs it to the high image quality monitor 95. If the aspect ratio needs to be converted, it is converted to 1: 1. When an HDTV monitor is used as an observation monitor, an image is synthesized so as to be converted to 1125 scanning lines and an aspect ratio of 16: 9, and output to the HDTV monitor. In addition, of the endoscope image signal and the X-ray image signal,
Those which do not need to convert the number of scanning lines or the like may be passed through a conversion circuit and synthesized as they are.

As described above, by selectively switching the number of scanning lines and the aspect ratio so as to correspond to a plurality of observation monitor systems and converting them, the endoscope observation image and the X-ray image can be changed according to the connected monitor. A fluoroscopic image can be synthesized and displayed.

Other structures, operations and effects are the same as those of the first embodiment.

[0054]

As described above, according to the present invention, when an object to be inspected is imaged by the optical image imaging means, X-ray irradiation may occur and X-ray irradiation noise may be mixed into the image signal. However, there is an effect that an image of a test site with less noise can be obtained by suppressing the mixed noise component.

[Brief description of the drawings]

FIG. 1 to FIG. 5 relate to a first embodiment of the present invention,
FIG. 1 is a block diagram showing the configuration of an endoscope / X-ray observation apparatus

FIG. 2 is an explanatory diagram showing a configuration of an image combining unit of the endoscope / X-ray observation apparatus.

FIG. 3 is a circuit diagram showing a configuration of a noise reduction circuit.

FIG. 4 is a characteristic diagram showing characteristics of the noise reduction circuit of FIG. 3;

FIG. 5 is a block diagram showing a configuration of a modified example of the noise reduction circuit.

FIG. 6 is an explanatory diagram showing a display screen of an observation monitor.

FIG. 7 is a block diagram showing a configuration of an endoscope / X-ray observation apparatus according to a second embodiment of the present invention.

FIG. 8 is a block diagram showing a configuration of an endoscope / X-ray observation apparatus according to a third embodiment of the present invention.

FIG. 9 is a block diagram showing an image synthesizing unit and a monitor connected to the image synthesizing unit according to a fourth embodiment of the present invention.

[Explanation of symbols]

 DESCRIPTION OF SYMBOLS 1 ... Endoscope 3 ... X-ray apparatus 4 ... Image synthesis part 5 ... Observation monitor 6 ... Video signal processing circuit 7 ... Scanning line conversion circuit 8 ... Image synthesis circuit 10 ... Endoscope image control device 12 ... Noise reduction circuit 58: Endoscope observation image 59: X-ray fluoroscopic image 72: Aspect ratio conversion circuit

────────────────────────────────────────────────── ─── Continuing on the front page (72) Inventor Yudai Nakagawa 2-43-2 Hatagaya, Shibuya-ku, Tokyo Inside Olympus Optical Co., Ltd. (72) Katsuyuki Saito 2-43-2 Hatagaya, Shibuya-ku, Tokyo Inside the Olympus Optical Co., Ltd. (72) Inventor Akihiro Miyashita 2-43-2 Hatagaya, Shibuya-ku, Tokyo Inside the Olympus Optical Co., Ltd. (72) Shinji Yamashita 2-43-2, Hatagaya, Shibuya-ku, Tokyo Inside the Olympus Optical Co., Ltd. (72) Inventor Akira Murata 2-43-2 Hatagaya, Shibuya-ku, Tokyo Inside the Olympus Optical Co., Ltd. Akiyoshi Ishikawa 2-43-2, Hatagaya, Shibuya-ku, Tokyo Olympus Optical Co., Ltd. (56) References JP-A-62-266025 (JP, A) JP-A-60-217783 (JP, A) (58) Field surveyed (Int.Cl. ⁷ , DB name) A61B 1/00-1/32 A61B 6/00-6/14 G02B 23/24-23/26

Claims (1)

(57) [Claims] An X-ray is irradiated from a predetermined X-ray irradiation device.
Optical image capture provided in an endoscope for observing a predetermined test site
Optical image pickup signal for inputting an optical image pickup signal from the image means
X-rays are radiated from an X-ray irradiating device , and X-ray transmission through the X-ray irradiating device is performed.
Inputs X-ray imaging signals from X-ray imaging means for capturing visual images
X-ray imaging signal inputting means, and an optical image imaging signal from the optical image imaging signal inputting means.
An X-ray imaging signal input from the X-ray imaging signal input means;
Signal synthesizing means for synthesizing signals and outputting a predetermined synthesized image signal
And inputting a combined imaging signal from the signal combining means and
First input / output circuit means for outputting with a first output characteristic, and a combined imaging signal from the signal combining means,
1 that suppresses the output of a signal at a lower level than the output characteristic of
A second input / output circuit means for outputting with an output characteristic of 2 and the first input / output circuit means or the second input / output circuit.
Based on the composite imaging signal output from the optical path means,
Generating a composite video signal obtained by synthesizing an image and the X-ray fluoroscopic image.
Video signal processing circuit, and the signal synthesizing means signal from the signal synthesizing means,
When the X-ray is irradiated from the X-ray irradiator, the first
To the X-ray irradiating device.
When no X-rays are emitted from the
An image pickup system , comprising: output switching means for outputting to the power circuit means .