JP3220501B2 - Endoscope / X-ray observation device - Google Patents

Description

DETAILED DESCRIPTION OF THE INVENTION

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to an endoscope / X-ray observation apparatus capable of displaying at least an endoscopic 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.

When the endoscope observation image and the X-ray fluoroscopic image are displayed on separate monitors as described above, the operation and diagnosis of the endoscope must be performed while alternately comparing the two monitors. Therefore, there is a problem that the operability is poor and the operator's fatigue is increased. Therefore, in order to solve the above-mentioned problem, an apparatus capable of displaying an endoscopic 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. I have. 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.

[0005]

However, when an endoscopic observation image and an X-ray fluoroscopic image are displayed on the same monitor or on separate monitors, the X-ray apparatus needs to obtain X-ray fluoroscopic images. When irradiating the X-rays, X-ray irradiation noise is mixed into the image signal processing device of the endoscope, etc., and a spot-like noise is generated in the endoscope observation image, resulting in an image which is very difficult to see. Was. In addition, the noise due to the X-ray irradiation is generated not only in the endoscope observation image but also on the entire screen of the display monitor, which may hinder the diagnosis. In addition, there is a problem that a circuit such as a diaphragm unit malfunctions due to mixing of noise due to X-ray irradiation, resulting in an image which is difficult to observe.

The present invention has been made in view of these circumstances, and an endoscope / X-ray observation apparatus capable of preventing the influence of noise due to X-ray irradiation and capable of obtaining a good image which is easy to observe. It is intended to provide.

[0007]

An endoscope X according to the present invention is provided.
The X-ray observation apparatus is configured to display an endoscopic observation image obtained by capturing an image of a test site with an endoscope and an X-ray fluoroscopic image obtained by irradiating the test site with X-rays. A mirror / X-ray observation apparatus, wherein an image signal obtained by imaging with the endoscope is provided.
And an X-ray fluoroscopic image signal from the X-ray observation apparatus.
Image synthesizing means, and a signal path including the image synthesizing means.
To suppress noise components in the input signal to be input.
Check that X-rays are being emitted from the X-ray observation device.
Further comprising a noise reduction means for performing in response to a signal indicating
It is characterized by .

[0008]

The noise reduction means suppresses noise components during X-ray irradiation, and an endoscopic observation image obtained by imaging with an endoscope and an X-ray obtained by irradiating X-rays to a test site. And a perspective image.

[0009]

Embodiments of the present invention will be described below with reference to the drawings. 1 to 9 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. 2 is a schematic configuration of the entire endoscope / X-ray observation device. 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 an explanatory diagram showing a display screen of an observation monitor, and FIG. FIG. 7 is a block diagram illustrating a configuration example of an aperture control unit in the endoscope imaging unit, FIG. 7 is an explanatory diagram illustrating a configuration example in a case where display of an endoscope image is turned on / off according to the presence or absence of X-ray irradiation, and FIG. FIG. 9 is an explanatory view showing a display screen of a monitor in the apparatus shown in FIG. 7, and FIG. 9 is a block diagram showing a configuration example when an enhancement circuit in the endoscope image control apparatus is changed according to the presence or absence of X-ray irradiation.

As shown in FIG. 2, an endoscope / X-ray observation apparatus comprises an endoscope 1 inserted into a subject, an X-ray irradiator 2 for irradiating the subject with X-rays, An X-ray imaging unit 4 that captures an X-ray fluoroscopic image. The endoscope 1 is connected to an endoscope image control device 10, and a signal of a subject image picked up by the endoscope 1 is processed to generate an endoscope observation image. The X-ray imaging unit 4 is connected to the X-ray device 3 so that an X-ray fluoroscopic image is generated. Further, the X-ray device 3 is connected to the endoscope image control device 10,
The endoscopic image control device 10 combines an endoscopic observation image and an X-ray fluoroscopic image.

The endoscope image control device 10 is configured as shown in FIG. In addition, the endoscope image control device 1
0 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.

[0013]

[Operation] In the above configuration, X-rays are emitted from the X-ray observation device.
Image synthesizing means according to a signal indicating that light is being emitted
Noise reduction means provided in the signal path including
A noise component in the input signal input to the noise reduction unit is suppressed, and an endoscopic observation image obtained by imaging with an endoscope and an X-ray obtained by irradiating a test site with X-rays. A fluoroscopic image is displayed.

The endoscope image control device 10 includes a light source unit 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 inputted 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. Further, an X-ray fluoroscopic image signal from the X-ray device 3 is input to the image synthesizing circuit 8.

The image synthesizing circuit 8 synthesizes the endoscopic image signal from the image memory 42 and the X-ray image signal obtained by the X-ray device 3 and outputs the synthesized signal to the D / A converter 43. The 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, is input to the emitter follower type transistor Q1, and is 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 signal through the noise reduction circuit 12 having the 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.

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 section 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 a color bar / 50% white generating 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. 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. A 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 digital signal is converted into a digital signal by an A / D converter 37 and stored in the image memory 42. The signal read from the image memory 42 is used for image synthesis. Input to the circuit 8. Also,
An X-ray fluoroscopic image signal captured by the X-ray imaging unit 4 and generated by the X-ray device 3 is input to the image synthesis circuit 8.

The image synthesizing circuit 8 synthesizes the endoscope image signal from the image memory 42 and the X-ray image signal from the X-ray apparatus 3, and the synthesized image signal is converted into an analog signal by the D / A converter 43. And input to the noise reduction circuit 12. When the image is synthesized by the image synthesis circuit 8,
In order for the image signal to be compatible with a system such as a monitor (for example, N
In the TSC system, the number of scanning lines is 525 and the aspect ratio is 4:
3) Convert the number of scanning lines, aspect ratio, etc.

In the noise reduction circuit 12, the transistor Q2 is turned on / off by an ON signal from the X-ray device 3,
As shown in FIG. 4, the coring curve is switched 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, and the endoscopic observation image and the X-ray fluoroscopic image are converted to the observation monitor. 5 is displayed.

As shown in FIG. 5, an endoscopic observation image 58 and an X-ray fluoroscopic image 5 are displayed on the screen of the observation monitor 5.
9 is displayed, but when the noise reduction circuit 12 is not operated, the endoscope 1, the endoscope image control device 10, and the transmission line of the endoscope image signal in FIG. For example, spot-like noise is mixed into the endoscope observation image 58 and the like as shown in FIG. However, by suppressing a noise component distributed in a low level range by the noise reduction circuit 12 during X-ray irradiation, a good image in which the noise component is suppressed can be obtained as shown in FIG. .

Also, if noise at the time of X-ray irradiation enters the aperture control unit of the endoscope imaging unit, the aperture malfunctions, causing hunting and the like, and the endoscope image becomes very difficult to observe. appear. Therefore, as shown in FIG.
With the configuration in which the aperture is switched to the fixed gain according to the presence or absence of the line irradiation, malfunction of the aperture can be prevented.

The reflected light from the subject forms an image on the image forming surface of the CCD 113 via the stop 111 and the objective lens 112 of the endoscope image pickup device. CCD 113,
It is controlled by a timing signal from the timing circuit 114, and the photoelectrically converted output signal from the CCD 113 is amplified by the amplifier circuit 115 and output as a video signal to the endoscope image controller. ing. Further, the timing circuit 114 transmits a synchronization signal for synchronizing to the endoscope image control device or the like.

The output of the amplifying circuit 115 is also supplied to an output circuit 116 which includes an integrating circuit and performs an averaging process. The signal averaged by the output circuit 116 is input to one input of a switching circuit 117 as an automatic aperture signal. It is supplied to the end. A luminance control signal for controlling the aperture with a fixed gain is supplied to the other input terminal of the switching circuit 117 from the outside (for example, an endoscope image control device). Here, as the value of the luminance control signal, an appropriate value may be set in advance, or the gain may be manually adjusted. The control input terminal of the switching circuit 117 includes:
An X-ray detection signal from the X-ray detection circuit 118 is input,
The input of the switching circuit 117 is switched according to the presence or absence of the line irradiation. Note that the X-ray ON signal described above may be used instead of the X-ray detection signal. Then, the automatic aperture signal or the brightness control signal from the switching circuit 117 is supplied to the aperture 111, and the aperture is controlled.

In this example, when X-ray irradiation is not detected by the X-ray detection circuit 118, that is, when X-rays are not irradiated, an automatic aperture signal from the output circuit 116 controls the aperture according to the brightness of the image signal. 111 is automatically controlled. On the other hand, at the time of X-ray irradiation, the switching circuit 117 is switched by an X-ray detection signal, a luminance control signal is input to the aperture 111, and aperture control is performed with a fixed gain.

As described above, by controlling with a fixed gain at the time of X-ray irradiation, malfunction of the diaphragm due to X-rays can be prevented, and a good endoscope image can be obtained.

As shown in FIG. 7, an image switching circuit 119 for switching an image signal in response to an X-ray ON signal may be provided so that only an X-ray image is displayed at the time of X-ray irradiation as shown in FIG. it can. Image switching circuit 119
Switches an image signal to be output to the monitor 5 in response to an X-ray ON signal. For example, as shown in FIG. 8A, during normal endoscope observation without X-ray irradiation, the endoscope image is displayed on the right side of the screen. The X-ray image is displayed in the half, and only the X-ray image is displayed in the left half of the screen at the time of X-ray irradiation. Also, as shown in FIG.
During normal endoscopic observation, only the endoscope image may be enlarged and only the X-ray image may be enlarged and displayed on the entire screen during X-ray irradiation.

As described above, by displaying only the X-ray image at the time of X-ray irradiation, it is possible to prevent noise from entering the endoscope image and malfunction of the circuit, and to always obtain a good image.

Further, as shown in FIG. 9, the enhancement circuit in the endoscope image control device can be changed according to the presence or absence of X-ray irradiation. When the enhancement circuit is operated during X-ray irradiation, the noise component is emphasized, and even if the noise component is suppressed by the noise reduction circuit 12, the noise of the image may be conspicuous. Therefore, the enhancement switching circuit 1
30 is provided, and an appropriate image is obtained by switching the enhancement circuit.

The endoscope image signal is stored in the main image frame memory 122 and the sub image frame memory 123 via the A / D converter 121. Also,
The X-ray image signal is sent to the main image frame memory 125 and the sub image frame memory 126 via the A / D converter 124.
It is stored in. Under the control of the image control device 128 based on the instruction from the input device 127, the writing to the frame memories 122, 123, 125, and 126 is performed, and the switching circuit 129 controls the main image frame memory 122 for the endoscope. X-ray sub-image frame memory 126, or X-ray main image frame memory 125 and endoscope sub-image frame memory 12
3 is selected, and the endoscope image and the X-ray image are combined. That is, the switching circuit 12
9 allows the user to select which of the endoscope image and the X-ray image is to be the main screen.

The output of the switching circuit 129 is converted to an analog signal by the D / A converter 43 in the same manner as in the configuration of FIG. 1, and then converted to a standard video signal by the video signal processing circuit 44. , An endoscope observation image and an X-ray fluoroscopic image are displayed. Here, an enhancement switching circuit 130 is provided in a stage preceding the video signal processing circuit 44, and an enhancement circuit (1) 131 in which the enhancement level is set high and an enhancement circuit (2) 132 in which the enhancement level is set low. , Three signal paths can be selected as they are.
An X-ray detection signal from the X-ray detection unit 101 is supplied to a control input terminal of the enhancement switching circuit 130, and an output path is switched according to the presence or absence of X-ray irradiation.

At the time of normal endoscopic image observation, the enhancement circuit (1) 131 is selected, and an enhancement effect such that an image suitable for endoscopic observation is obtained. On the other hand, when X-ray irradiation is detected by the X-ray detecting means 101 (X-ray irradiation is performed), either the enhancement circuit (2) 132 or the passage is selected depending on the intensity of X-ray irradiation, and the enhancement effect is reduced. Is suppressed. That is, when the X-ray irradiation is weak, the enhancement circuit (2) 132 performs enhancement at a low level, and when the X-ray irradiation is strong, the image signal passes as it is.

As described above, by selectively switching the enhancement circuit in accordance with the irradiation of X-rays, it is possible to obtain a good image free from the influence of noise without emphasizing the noise component.

As described above, according to the present embodiment, in the apparatus for displaying an endoscopic observation image and an X-ray fluoroscopic image,
By suppressing the noise component at the time of irradiating the X-ray, it is possible to prevent the noise from being mixed into the image signal due to the X-ray irradiation and the influence of the noise such as a malfunction of the circuit, and to obtain a good image which is easy to observe.

In the first embodiment, the endoscope image control device is constituted by a simultaneous system, but may be constituted by a frame sequential system as shown in FIG. Here, the first
The same reference numerals are given to the same components as those in the embodiment, and the description is omitted.

The light source unit 28 of the endoscope image control device is provided with a rotary filter 71 in addition to the configuration described in the first embodiment. The rotation filter 71 has red (R), green (G),
Color separation filters 72R and 72 that transmit blue (B) color
G, 72B are provided in a circular shape, and the color transmission filters 72R, 72G, 72B are sequentially arranged on the optical path connecting the light source lamp 33 and the incident end face of the light guide 27 to the motor 73.
And is inserted by being rotationally driven.

The signal processing section 31 is a solid-state image sensor 21.
A variable gain amplifier 74 that receives an image signal from the digital camera is provided. The gain of the variable gain amplifier 74 is adjusted by a control signal from the white balance control circuit 41. The gain-adjusted image signal is A
The signal is converted into a digital signal by the / D converter 37, and is stored in the R memory 76.
After being written into the R, G memory 76G and B memory 76B, they are sequentially read and input to the image synthesizing circuit 8. Each image memory 7 in the image synthesizing circuit 8
The endoscope image signals from the 6R, 76G, and 76B and the X-ray image signal from the X-ray device 3 are synthesized, and the D / A converter 43
The noise reduction circuit 12 suppresses a noise component distributed in a low level range during X-ray irradiation. Other configurations are the same as in the first embodiment.

In the above configuration, the illumination converted into the R, G, and B color lights by the rotary filter 71 is applied to the incident end face of the light guide 27, and the light distribution lens system 19 illuminates the test site 22. The reflected light from the test site 22 forms an image on the imaging surface of the solid-state imaging device 21. In this case, the solid-state imaging device 21 is a solid-state imaging device for monochrome images. The solid-state imaging device 21 is driven by a CCD driver 24, and outputs R,
G and B plane-sequential image signals are output. The white balance control circuit 41 controls the gain of the variable gain amplifier 74 according to each of R, G, and B timings based on the RGB timing signal from the memory controller 53 so that the signal output of the variable gain amplifier 74 becomes R = G = B. And take a white balance. Then, the A / D converter 37
The digital signal is written into the R memory 76R, the G memory 76G, and the B memory 76B, and sequentially read out by the RGB timing signal from the memory controller 53 and input to the image synthesizing circuit 8. In the endoscope observation image and the X-ray fluoroscopic image synthesized by the image synthesis circuit 8, the noise component distributed in a low level range at the time of X-ray irradiation is suppressed by the noise reduction circuit 12, as in the first embodiment. It is displayed on the observation monitor 5.

As described above, in the field sequential apparatus, similarly, the endoscope observation image and the X-ray fluoroscopic image can be synthesized and displayed, and the contamination of noise at the time of X-ray irradiation can be prevented. A good image that can be easily observed can be obtained.

FIG. 11 is a block diagram showing a configuration of a noise reduction circuit according to a second embodiment of the present invention.

The second embodiment is an example in which a circuit for digitally canceling noise is used as a noise reduction circuit.

The digital noise reduction circuit 12a is composed of a recursive filter. A subtraction circuit 62 for taking the difference between the current input signal and the signal of one frame before, a frame memory 63 for storing the signal of one frame before, and a coefficient circuit for multiplying the input signal by k (where 0 ≦ k ≦ 1) 64, a coefficient circuit 65 for multiplying the output of the subtraction circuit 62 by (1-k),
An addition circuit 66 for adding the outputs of the coefficient circuits 64 and 65 is provided. A signal from which noise components have been removed is output from the addition circuit 66 and stored in the frame memory 63. When the digital noise reduction circuit 12a is used, the noise reduction circuit 12a is provided before the D / A converter 43 in the configuration of FIG. Other configurations are the same as in the first embodiment.

In FIG. 11, the input signal is subtracted by a subtractor 62.
, The difference from the signal one frame before stored in the frame memory 63 is obtained, and the coefficients k and 1-k of the coefficient circuits 64 and 65 are set according to the magnitude of the difference. 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,
The two are added by the adder circuit 66 to output a signal from which noise components have been removed, and the signal is stored in the frame memory 63. Similar operations are repeated for the subsequent frames, and an image signal from which noise components have been removed is obtained.

As described above, even when the digital noise reduction circuit 12a is used, like the noise reduction circuit using the analog coring circuit of the first embodiment, X
It is possible to suppress noise components due to line irradiation, and it is possible to obtain a good image with less noise.

FIG. 12 is an explanatory view showing an operation unit of an X-ray apparatus according to a third embodiment of the present invention and a noise reduction circuit connected thereto.

The third embodiment is an example in which the amount of noise reduction is varied according to the intensity of the X-ray irradiation. The X-ray apparatus 3 is provided with an X-ray irradiation variable volume 81 on the operation unit of the front panel, and the intensity of the X-ray emitted from the X-ray irradiation unit 2 is set by the variable irradiation dose volume 81. It is supposed to be. At this time, an intensity setting signal is output from the X-ray device 3, and this signal is also input to the noise reduction circuit 12. The strength setting signal is V / F converted (voltage /
A frequency signal subjected to frequency conversion may be used.

The noise reduction circuit 12 varies the coring curve shown in FIG. 4 according to the strength setting signal to increase or decrease the amount of noise reduction. At this time, in FIG.
By making the values of 1, r3, r4, r5, and r7 variable, the low-level signal range changes, and the amount of noise reduction increases or decreases. For example, when the X-ray irradiation amount is weak, the coring curve is made closer to linear to reduce the noise reduction amount, and when the X-ray irradiation amount is strong, the low-level signal range of the coring curve is expanded to reduce the noise reduction amount. More. In this way, by varying the amount of noise reduction in accordance with the amount of X-ray irradiation and performing appropriate noise reduction, it is possible to prevent signal components of a low level from being suppressed more than necessary and prevent image quality from deteriorating. And a good image can always be obtained.

When a digital noise reduction circuit is used as in the second embodiment, the coefficient circuits 64 and 65 are used.
Is varied according to the strength setting signal to increase or decrease the noise reduction amount.

As described above, it is possible to appropriately reduce noise by adjusting the noise reduction amount according to the amount of X-ray irradiation, and it is possible to always obtain a good image by preventing deterioration in image quality. Become. Other configurations, operations, and effects are the same as those of the first embodiment.

FIGS. 13 and 14 relate to a fourth embodiment of the present invention. FIG. 13 is a block diagram showing the configuration of an endoscope / X-ray observation apparatus, and FIG. 14 is a block diagram showing a modification of the isolation means. It is.

The fourth embodiment is an example in which the signal line from the X-ray apparatus 3 is not directly connected to the image synthesizing unit but is connected via an isolation means. The endoscope image signal generated by the endoscope image control device 10 is transmitted to the A / D converter 9.
The digital signal is converted into a digital signal at 1 and temporarily stored in an endoscope image memory 92 before being input to an image synthesizing circuit 93.

On the other hand, the X-ray image signal generated by the X-ray device 3 is supplied to the A / D converter 9 via the isolation means 94.
5 and temporarily stored in the X-ray image memory 96, and then to the image synthesizing circuit 93.
That is, the image signal is transmitted in a state where the signal line is separated from the X-ray apparatus 3, the X-ray image memory 96, and the image synthesizing circuit 93 by the isolation means 94. As the isolation means 94, for example, a high-speed analog photocoupler is used. Further, as shown in FIG. 14, an FM modulation circuit 97 and an FM demodulation circuit 99 may be provided before and after the isolation means 98, and a signal line may be separated by modulating / demodulating an FM signal. In this case, the isolation means 9
A digital photocoupler, pulse transformer, or the like is used as 8.

The image synthesizing circuit 93 converts the scanning line, the aspect ratio and the like in the same manner as in the first embodiment, and
After synthesizing with the line image and converting it into an analog signal by the D / A converter 43, the synthesized image signal is converted into a video signal processing circuit 44.
The video signal is converted into a standard video signal, and an endoscopic observation image and an X-ray fluoroscopic image are displayed on the observation monitor 5.

As described above, by separating the signal line from the X-ray device by the isolation means, C
It is possible to prevent the noise of the X-ray apparatus from being mixed into a signal processing circuit or an image synthesizing circuit of an endoscope that handles a weak signal from a CD, and to display an endoscopic observation image and an X-ray fluoroscopic image in a device. And a good image with less noise can be obtained.

FIG. 15 is a block diagram showing a configuration of an endoscope / X-ray observation apparatus according to a fifth embodiment of the present invention.

The fifth embodiment is an example in which the isolation means of the fourth embodiment is provided in a device for displaying an X-ray image in accordance with the presence or absence of X-ray irradiation. The X-ray apparatus 3 is connected to an X-ray image memory 96 and an image synthesizing circuit 93 via an isolating means 94 in the same manner as in the fourth embodiment, so as to be synthesized with an endoscope image. Further, an X-ray detecting unit 101 is provided near the X-ray imaging unit 4, and the X-ray detecting unit 10 is provided.
1 is connected to an X-ray detection circuit 103 via an isolation means 102 so that the presence or absence of X-ray irradiation is detected. The X-ray detection signal from the X-ray detection circuit 103 is input to the control circuit 104, and the control circuit 104 sends a control signal to the image composition circuit 93 based on the X-ray detection signal. The image synthesizing circuit 93 switches an image synthesizing operation according to a control signal from the control circuit 104. That is, the X-ray detecting means 10
1. When X-ray irradiation is detected by the X-ray detection circuit 103, the endoscope image from the endoscope image control device 10 and the X-ray
An X-ray image from the X-ray device 3 is synthesized, and an endoscopic observation image and an X-ray fluoroscopic image are displayed on the monitor 5. On the other hand, when X-ray irradiation is not detected, only the endoscopic observation image from the endoscopic image control device 10 is displayed on the monitor 5.

Here, since the signal lines of the X-ray detection means 101 are separated by the isolation means 102, noise due to X-rays does not enter the image synthesizing circuit 93 and the like. Therefore, the presence or absence of X-ray irradiation is detected and X
Even in a device that synthesizes and displays an endoscope image and an X-ray image in accordance with the irradiation of radiation, it is possible to prevent mixing of noise due to X-rays and obtain a good image with less noise as in the fourth embodiment. Can be.

[0068]

As described above, according to the present invention, X
There is an effect that the influence of noise due to the line irradiation can be prevented, and a good image that can be easily observed can be obtained.

[Brief description of the drawings]

FIG. 1 to FIG. 9 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 schematic configuration of the entire 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 an explanatory diagram showing a display screen of an observation monitor.

FIG. 6 is a block diagram illustrating a configuration example of an aperture control unit in the endoscope imaging unit;

FIG. 7 is an explanatory diagram showing a configuration example in a case where display of an endoscope image is turned on / off according to presence / absence of X-ray irradiation;

FIG. 8 is an explanatory diagram showing a display screen of a monitor in the device of FIG. 7;

FIG. 9 is a block diagram showing a configuration example when an enhancement circuit in the endoscope image control device is changed according to the presence or absence of X-ray irradiation;

FIG. 10 is a block diagram showing a modification in which the endoscope image control device according to the first embodiment is configured by a frame sequential method;

FIG. 11 is a block diagram showing a configuration of a noise reduction circuit according to a second embodiment of the present invention.

FIG. 12 is an explanatory diagram showing an operation unit of an X-ray apparatus according to a third embodiment of the present invention and a noise reduction circuit connected to the operation unit.

FIGS. 13 and 14 relate to a fourth embodiment of the present invention, and FIG. 13 is a block diagram showing a configuration of an endoscope / X-ray observation apparatus.

FIG. 14 is a block diagram showing a modification of the isolation means.

FIG. 15 is a block diagram showing a configuration of an endoscope / X-ray observation apparatus according to a fifth embodiment of the present invention.

[Explanation of symbols]

 DESCRIPTION OF SYMBOLS 1 ... Endoscope 2 ... X-ray irradiation part 3 ... X-ray apparatus 4 ... X-ray imaging part 5 ... Observation monitor 8 ... Image synthesis circuit 10 ... Endoscope image control device 12 ... Noise reduction circuit 58 ... Endoscope Observation image 59: X-ray fluoroscopic image

──────────────────────────────────────────────────続 き Continuing on the front page (72) Inventor Masahito Goto 2-43-2 Hatagaya, Shibuya-ku, Tokyo Inside Olympus Optical Industrial 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-2-68027 (JP, A) JP-A-59-103642 (JP, A) JP-A-57-117825 (JP, A) (58) Fields investigated (Int. Cl. ⁷ , DB name) A61B 1/00-1/32 A61B 6/00-6/14

Claims (1)

(57) [Claims] 1. An endoscope for displaying an endoscopic observation image obtained by capturing an image of a test site with an endoscope and an X-ray fluoroscopic image obtained by irradiating the test site with X-rays. A mirror / X-ray observation apparatus, wherein an image signal obtained by imaging with the endoscope and the X-ray
Image synthesis for synthesizing X-ray fluoroscopic image signals from an observation device
Means provided in a signal path including the image synthesizing means.
Suppression of noise components in the input signal to be
In response to a signal indicating that X-rays are being
The endoscope · X-ray observation device Nau and noise reduction means, comprising the.