JP3353949B2 - 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 a signal processing apparatus capable of performing signal processing for probes of different imaging systems by attaching a dedicated adapter to a signal processing apparatus main body in accordance with a probe such as an electronic scope to be used. The present invention relates to an imaging system including a device.

[0002]

2. Description of the Related Art In recent years, an endoscope capable of observing a diseased part or the like illuminated from a distal end portion of an insertion portion through an objective lens provided in an observation window by inserting an elongated insertion portion into a body. Has become widely used.

Further, by using an electronic endoscope in which an image pickup device such as a CCD is arranged on a focal plane of an objective lens, a signal processing device performs signal processing on a signal photoelectrically converted by the image pickup device, thereby forming a subject image on a monitor. An electronic endoscope system capable of displaying is also in practical use.

[0004] In the case of an electronic endoscope, if the number of pixels of the image pickup device is different, it is necessary to change the signal processing of the signal processing device. Japanese Patent Application Laid-Open No. 63-260527 discloses a conventional electronic endoscope. The signal processor unit is unitized in accordance with the number of pixels, and a dedicated unit is attached and used in accordance with the electronic endoscope having a different number of pixels, so that the electronic endoscope having a different number of pixels can be supported. An electronic endoscope system is disclosed.

[0005]

However, the imaging method of the electronic endoscope is a simultaneous method for obtaining a color image under white illumination and a simultaneous illumination method for sequentially illuminating with illumination light in different wavelength ranges. And a frame sequential method for obtaining a color image to be picked up by the camera. The preceding example can cope with a case where the number of pixels is different, but cannot cope with a case where the imaging method is different.

In the case where the imaging system is different, if the entire signal processing apparatus is replaced, the cost increases. Therefore, there is a demand for a system which can cope with the case where the imaging system is different with a small cost.

[0007] In other words, if the system configuration is such that an electronic endoscope having a different imaging method can be selectively used in accordance with the situation of the endoscopic examination / diagnosis, the merit due to the difference in the imaging method can be enjoyed. Endoscopy / diagnosis becomes possible.

For example, if a simultaneous method of obtaining a color image under white illumination is adopted, even when a subject with a large motion is imaged, color misregistration rarely occurs, so that an organ near the heart is examined. / Effective when diagnosing.

On the other hand, in the case of examining / diagnosing a part in a narrow lumen with little movement of an organ away from the heart or a small intraluminal part, adopting a frame sequential method is about three times as large as that of the simultaneous method. An endoscope image having a resolution can be obtained (assuming that an image sensor having the same size is used in the simultaneous method and the frame sequential method). Therefore, there is a merit that a fine abnormal portion can be identified even for an affected part having an initial symptom with little change from a normal state.

[0010] On the other hand, if only an electronic endoscope of the frame sequential type can be used when examining / diagnosing an organ near the heart, there is a possibility that an endoscope image having a color shift will occur. In this case, even if an electronic endoscope having a different number of pixels is used as in the conventional example, it cannot be improved. In addition, when examining / diagnosing a site in a narrow lumen, it is difficult to obtain a high-resolution image if only a simultaneous electronic endoscope can be used. In this case, if an electronic endoscope having a large number of pixels is used,
Although the resolution can be improved, the size of the imaging device becomes large, so that it becomes difficult to insert the imaging device into a narrow lumen.

Therefore, in order to obtain more effective endoscopy / diagnosis results, it is desired that a system which can be selectively used from electronic endoscopes having different imaging methods as described above can be realized at low cost. Further, the above conventional example is also applicable to a case where an ultrasonic scope that obtains an ultrasonic image different in type from an image obtained by photoelectrically converting an optical image obtained by an electronic endoscope, and a system that can selectively use an electronic endoscope. I can't deal with it.

An image pickup system that can be used with an ultrasonic scope that can obtain acoustic image information different from optical image information obtained by an electronic endoscope for an object to be inspected, such as an affected part, can be used for examination / diagnosis. Effective information can be obtained.
Further, the system configuration can be changed from the electronic endoscope system as needed at a low cost, and a system configuration suitable for inspection / diagnosis can be a very effective system for inspection / diagnosis.

The present invention has been made in view of the above points, and provides an imaging system capable of coping with a probe provided with an imaging element having a different imaging method with a minimum necessary change and reducing the cost. It is intended to be.

[0014]

SUMMARY OF THE INVENTION According to the present invention,
An imaging system includes a first probe having an elongated first insertion portion, a first imaging unit provided on a distal end side of the first insertion portion, and taking an image of an object, and an elongated second insertion portion. A second probe provided on the distal end side of the second insertion portion, the second probe having a different imaging method from the first imaging device, and the second probe; A first adapter unit that is connected via a cable and generates a drive signal compatible with the imaging method of the first imaging unit, and is connected to the second probe via a cable;
A drive signal suitable for the imaging method of the second imaging means is generated, and a second drive signal separate from the first adapter unit is generated.
An adapter unit, and a connection portion to which the first and second adapter units are selectively detachably connected,
The dry supply to the first and second imaging means;
A main unit for transmitting a synchronization signal for generating a video signal, performing signal processing suitable for the first and second imaging means, and generating a standard video signal, and connected to the main unit. , made monitor Toka et structure for displaying the image signal, for the case the imaging system is different probes, only replacing the adapter unit, and to accommodate.

[0015]

Embodiments of the present invention will be described below with reference to the drawings. FIGS. 1 to 6 relate to a first embodiment of the present invention, FIG. 1 is an overall configuration diagram of an electronic endoscope system according to a first embodiment of the present invention, and FIG. 2 is a configuration of a simultaneous type electronic endoscope system. FIG. 3 is a block diagram showing a configuration of a frame sequential type electronic endoscope system, FIG. 4 is a block diagram showing a configuration of a signal conversion circuit, FIG. 5 is a block diagram of a frame sequential type light source device,
FIG. 6 is an explanatory diagram showing output signals of the drive signal generation circuit.

As shown in FIG. 1, an electronic endoscope system 1 according to a first embodiment has an electronic endoscope (hereinafter, referred to as an image pickup system) having a different imaging method.
2A, 2B and electronic scope 2
Light source devices 3A and 3B for supplying illumination light suitable for A and 2B, adapters 4A and 4B for outputting drive signals suitable for electronic scopes 2A and 2B, and adapters 4A and 4B dedicated to electronic scopes 2A and 2B. Is detachably mounted and has a signal processing device main body (also referred to as a video processor main body) 5 for performing almost common signal processing, and a color monitor for displaying a standard video signal output from a signal output terminal of the video processor main body 5. 6 and a VTR 7 connected to the video processor main body 5 and serving as a peripheral device.

The electronic scopes 2A and 2B are provided at an elongated and flexible insertion portion 8 and at the base end of the insertion portion 8.
It has a thickened operation unit 9 and a flexible universal cable 11 extending from the operation unit 9, and a connector 12 provided at the end of the universal cable 11 is detachably attached to the light source devices 3A and 3B, respectively. It can be installed with.

The insertion portion 8 is formed at the front end portion 13 in which the image pickup means is stored, at the rear end of the front end portion 13, and is formed at the rear end of the bending portion 14 which is freely bendable. And a long flexible tube portion 15. By connecting one connector 17 of the signal cable 16 to the connector 12, the other connector 18 can be detachably attached to the connector receivers 19A and 19B of the adapters 4A and 4B.

A recess 21 for accommodating the adapters 4A and 4B is provided on the front surface of the video processor main body 5, and a connector 22 provided on the back surface of the adapters 4A and 4B is detachably mounted inside the recess 21. A connector receiver 23 (omitted in FIG. 1) is provided.

The electronic scopes 2A and 2B used in the first embodiment have different imaging methods.
A has simultaneous imaging means for performing color imaging under illumination of white light, and the other electronic scope 2B has a field sequential light method for performing color imaging under sequential illumination light in three wavelength ranges. Imaging means.

When the system 1 shown in FIG. 1 is used with the simultaneous type electronic scope 2A, the simultaneous type electronic endoscope system 1A can be constituted by the combination shown in FIG. When used in the field-sequential type electronic scope 2B, the field-sequential type electronic endoscope system 1B can be configured by the combination shown in FIG.

As shown in FIG. 2, a light source lamp 24 and a condenser lens 25 are provided inside the light source device 3A.
The white illumination light emitted by the light source lamp 24 is
And is supplied to the end face of the light guide fiber 26 at the end of the universal cable 11. The supplied illumination light is transmitted by the light guide fiber 26 to the end face of the insertion portion 8 on the distal end portion 13 side, and further transmitted to the distal end portion 1.
The light is emitted toward the subject 28 through an illumination lens 27 attached to the illumination window 3.

An optical image of the subject 28 illuminated with the illumination light emitted from the illumination window is formed on the photoelectric conversion surface of the CCD 31 disposed on the focal plane by an objective lens 29 attached to the observation window of the distal end portion 13. A single-chip color chip 32 of a mosaic color filter array for color separation is attached to a photoelectric conversion surface of the CCD 31. The CCD 31 converts an optical image color-separated for each pixel by the single-chip color chip 32 into a photoelectric signal. Convert.

The adapter 4A houses a CCD drive signal generation circuit 33A (hereinafter simply referred to as a drive signal generation circuit) for mounting the single-chip color chip 32 and driving the CCD 31. The drive signal generation circuit 33A
Is applied to the CCD 31 to read out the photoelectrically converted video signal. The adapter 4A contains pre-processing means for pre-processing the CCD output signal as described below.

That is, the CCD output signal is amplified by the preamplifier 34 housed in the adapter 4A and then input to the CDS circuit 35, where unnecessary signals such as a transfer clock carrier are removed, and the video signal component is separated and extracted. You. This C
The output signal of the DS circuit 35 is input to a color separation circuit 36,
The color signal is separated into a luminance signal Y and a color signal C, and the luminance signal Y and the color signal C (more specifically, the color signal C is a color difference signal RY / B-
Y (representing Y) and input into the video processor main body 5 functioning as a common signal processing system.

In the adapter 4A, there is provided a CCD which forms an image pickup means connected to the adapter 4A and used.
The ROM 37A stores information for driving the drive 31 and information for performing signal processing suitable for the video signal output from the adapter 4A. By attaching the adapter 4A to the video processor body 5, the ROM 3
The information of 7A is stored in a decision circuit 38 in the video processor main body 5.
And is used for signal processing in the video processor main body 5.

The video processor main body 5 houses a power supply 41, and the power supply 41
In addition to supplying power to the secondary circuit system (each of the circuits), a power supply for the patient circuit system, which is isolated from the power supply for the secondary circuit system, is also provided. Circuit of each patient circuit system (that is,
Drive signal generation circuit 33A to color separation circuit 36,
The ROM 37A belongs to a secondary circuit system, and operates a drive power supply (not shown) supplied from a power supply for the secondary circuit system.

The synchronizing signal generator 42 housed in the video processor main body 5 is used to output horizontal and vertical synchronizing signals HD and VD.
And through the first isolation circuit 43,
It is supplied to the CCD drive signal generation circuit 33A in the adapter 4A. CCD signals are generated by these synchronization signals HD and VD.
The drive signal generation circuit 33A generates a dedicated drive pulse for driving the simultaneous type CCD 31 (CCD 31 having the color chip 32).

The luminance signal Y output from the color separation circuit 36
And the color signal C are insulated and separated from the patient circuit system through the second isolation circuit 44 to form a secondary circuit system.
After being input to the / D conversion circuit 45 and converted into a digital signal, it is input to the signal conversion circuit 46.

As shown in FIG. 4, for example, the signal conversion circuit 46 includes a memory section 46a (three memories 46-1, 46-2, 46-3) used for synchronizing a video signal, displaying a frozen image, and the like. , A color matrix conversion circuit 46b for performing conversion into RGB signals, and an AGC circuit 4 for performing AGC processing
6c, a gamma correction circuit 46d for performing gamma correction, a memory controller 46e for controlling writing / reading to / from the memory unit 46a, and a switch 46f for selecting a signal input to the memories 46-2 and 46-3. And performs signal conversion processing on the input signal,
Outputs the B signal.

When the switch 46f is of the simultaneous type, the contact b is selected as shown in FIG. 4, and the color difference signals RY / BY are inputted to the memories 46-2 and 46-3, and in the case of the frame sequential type. , A contact a is selected, and R, G, and B signals are input to three memories 46-1, 46-2, and 46-3.

The memory section 46a has a storage capacity for one frame of a color image in the case of the frame sequential type. In the case of the simultaneous type, the number of pixels for one frame of the color image is 1/3 that in the case of the frame sequential type, so that writing to the memory unit 46a and reading out from the memory unit 46a are 1/3 the number of pixels. This is done by specifying the memory address corresponding to the minute. Also,
In the case of the frame sequential type, the color matrix conversion circuit 46b outputs through without any conversion since the input signal is already an RGB signal. When generating the RGB signals, the switch 4 is used by using the determination information of the determination circuit 38.
6f, controls the color matrix conversion circuit 46b.

The RGB signal output from the signal conversion circuit 46 is converted into an analog signal by the D / A conversion circuit 47, and then the outline component of the signal is emphasized by the outline emphasis circuit 48.
The outline-enhanced RGB signal is supplied to a video buffer circuit 49.
, A standard video signal is output to the external monitor 6 together with the synchronization signal passed through the buffer circuit 50. Then, the color monitor 6 displays the subject image in color.

For example, the B signal whose outline has been emphasized is mixed by the adder 55a with the index information determined by the determination circuit 38, and the index information (for example, whether the scope is a simultaneous type or the adapter 4) is displayed on the color monitor 6.
A, etc.) are displayed. The RGB signal whose contour has been corrected is input to the encoder 51 together with the synchronizing signal,
The video signal is converted into a video signal of the SC system, and the video signal of the NTSC system is also transmitted via the video buffer 52 to, for example, a VTR.
7 to record a video signal.

Note that the output of the encoder 51 is also
At b, the index information of the discrimination circuit 38 is mixed and output. An operation panel 53 is provided on, for example, a front surface of the video processor main body 5.
Reference numeral 3 denotes a switch button for setting the color tone and the amount of contour enhancement of the image to suit the operator's preference. An operation signal when the operation panel 53 is operated is input to the CPU 54.

The CPU 54 identifies the operation signal,
The operating conditions / operating characteristics of the signal conversion circuit 46 and the outline emphasizing circuit 48 can be changed. When the operation of changing the color tone is performed, the CPU 54 executes, for example, FIG.
The color tone is changed by changing the characteristics of the AGC circuit 46c.

An ON signal for operating the freeze switch 55 of the electronic scope 2A is output to the C through the adapter 4A.
When the ON signal is input to the PU 54 and the CPU 54 detects this ON signal, the memory unit 46 a forming the signal conversion circuit 46 is set in a frozen state, and controls to output the frozen video signal to the monitor 6 side. In this case the CPU
Reference numeral 54 denotes a memory unit 4 for the memory controller 46e.
A write inhibit control signal is output to 6a.

The memory controller 46e is connected to the memory unit 4
A write disable signal is applied to the memory unit 4a.
6a holds the image before the write enable signal. The stored image is repeatedly displayed on the monitor 6 as a still image. On the other hand, when the field sequential type electronic scope 2B is used, the configuration of the field sequential type electronic endoscope system 1B shown in FIG. 3 is obtained.

The plane sequential type electronic scope 2B is the same as the simultaneous type electronic scope 2A of FIG.
A CCD 31 without 2 is used. That is, the photodiode array serving as the photoelectric conversion unit and the transfer unit have the same structure, and therefore can be driven by almost the same drive signal. In this embodiment, for example, an interline transfer type CCD 31 is employed.

The light source device 3B is the light source device 3A of FIG.
, A color filter disk 57 that is rotationally driven by a motor 56 is arranged in the illumination optical path of the lamp 24 and the lens 25. As shown in FIG. 5, the color filter disk 57 has R, G, and B light transmitting in the circumferential direction of the disk.
G, B transmission filters 58R, 58G, 458 are respectively attached, and R, G, B transmission filters 58R, 58G, 58B are sequentially interposed in the illumination light path to guide the R, G, B plane sequential light. 26.

The motor 56 is connected to the motor drive circuit 5
9 controls to rotate at a constant rotation speed. The motor drive circuit 59 is supplied with the vertical synchronization signal VD from the synchronization signal generator 42 housed in the video processor main body 5 via the adapter 4B. Rotate and drive synchronously.

Simultaneous and field sequential type electronic scope 2A
In both cases 2B and 2B, when the CCD 31 is of the interline transfer type, the drive signal generating circuit 33B in the adapter 4B generates the transfer signal TS shown in FIG. 6B at the end of each of the R, G and B illumination periods shown in FIG. 6A, for example. After transferring to the next vertical transfer register, the vertical and horizontal transfer signals φ shown in FIG.
V & φH is applied to the CCD 31. The vertical transfer signal φV and the horizontal transfer signal φH are output by the number of vertical pixels and the number of horizontal pixels, respectively.

In the case of the simultaneous type, the transfer signal TS is as shown in FIG. 6d, and the vertical and horizontal transfer signals φV & φH are as shown in FIG. 6e. 3 cycles.

Therefore, the simultaneous CCD drive signal generation circuit 33A generates the vertical and horizontal transfer signals φV & φH only for ３ period in the transfer signal generation circuit of the CCD drive signal generation circuit 33B in the case of the frame sequential method, for example. (For example, after generating the vertical and horizontal transfer signals φV & φH only during the 1/3 period, generation is prohibited until the next transfer signal TS). Alternatively, a divide-by-3 circuit for dividing the frequency by three may be added, and the horizontal transfer signal φV & φH may be generated by the number of vertical and horizontal pixels at the output of the divide-by-3 circuit.

As described above, when the common CCD 31 is employed, the two CCD drive signal generation circuits 33A and 33B
Can increase the number of parts that can be shared, thereby reducing costs. FIG.
As shown in the figure, the output signal of the CCD 31 is
Time series (serial) R / G / B via CDS circuit 35
Signal. That is, the signal becomes an R / G / B signal generated under the illumination light of each wavelength range, and is input to the isolation circuit 44 in the video processor main body 5 through one signal line (in the case of the simultaneous type). Will have two systems).

In the case of the frame sequential type, the other signal line is not used for signal transmission. Isolation circuit 4
The signal isolated by the A / D conversion circuit 45
After being subjected to A / D conversion, the signal is input to the signal conversion circuit 46. Discrimination circuit 3 for discriminating information in ROM 37B
8, the signal conversion circuit 46 converts the serial R / G / B signal into memories 46-1, 46-2, 46-3.
, And the stored R, G, B signals are read out and synchronized at the same time, passed through the color matrix conversion circuit 46b, and passed through the AGC circuit 46c and the γ correction circuit 46d to be converted by the D / A conversion circuit 47. It is converted to an analog RGB signal.

The steps after the D / A conversion circuit 47 are the same as those in FIG. However, the index information displayed on the color monitor 6 is different from that in FIG. According to the first embodiment,
The video signal generated by signal processing can be handled by the common video processor main body 5 only by attaching and detaching the adapters 4A and 4B to the electronic scopes 2A and 2B of the simultaneous system and the frame sequential system. Can be displayed with.

That is, a simultaneous type and a frame sequential type system can be selectively used according to the environment to be used, and an appropriate endoscopic inspection can be performed. For example, when observing a part with large movement, an image without color shift can be obtained by using a simultaneous system. On the other hand, if the frame sequential method is adopted for a part with little movement, the CC of the same number of pixels as the simultaneous method can be used.
Even if D is used, an endoscopic image having a resolution approximately three times as high as that obtained can be obtained, and fine parts can be identified.

Further, this embodiment has an advantage that a desired system can be constructed at low cost, and a system of a different imaging system can be reconnected and a different signal processing system can be provided compared to a case where the signal processing device is not divided into an adapter and a video processor main body. Work is easier than in the case of

Simultaneous and plane-sequential electronic scope 2
The background for selectively using A and 2B will be further described. For example, when an electronic scope is used clinically, the first examination is performed using a highly versatile simultaneous electronic scope for routine use. However, depending on the case, a biopsy or various procedures (for example, using a forceps to remove a polyp). It is often the case that the patient is removed or the treatment is continued with an electric scalpel or laser.

In such a case, it is necessary to replace the treatment tool of the electronic scope or the through hole (channel) for the forceps with one having a larger diameter. Is used, the number of pixels of the CCD is reduced, the resolution is reduced, or the output screen area is reduced, and observation with the same quality (same image quality) is not possible. Impossible. In this case, it is preferable to use a plane-sequential electronic scope because the same quality image can be obtained with a small number of pixels.

Therefore, if the video processor itself needs to be replaced, it is necessary to reconnect all the peripheral devices such as the monitor 6, the VTR 7, and the photographing device.
It is very time-consuming. In this case, two video processors for the simultaneous type and the frame sequential type are prepared, and the connection state is set to one.
It is conceivable to use switches and peripheral devices that can be switched at a time, but preparing two video processors is uneconomical in terms of money and space. This is because, as can be seen from the inside of the video processor main body 5 shown in FIG. 2 or FIG. 3, a large number of blocks are commonly used. Patient circuits that are particularly specific to medical equipment, 2
The isolation and power supply circuits which are distinguished from the next circuit are blocks occupying a large area and heavy.

Further, a synchronizing signal generating circuit and a video buffer for outputting an image to a monitor and each peripheral video device, and an A / D,
Each video signal processing including the D / A interface (γ, A
GC and contour emphasis) are expensive blocks including an electronic scope. On the other hand, according to the present embodiment, the adapter 4
Since it can be dealt with simply by exchanging the light source devices 3A and 3B with the light sources 3A and 3B, there is an advantage that no labor is required and the economical burden can be reduced.

In this embodiment, a part which can be used in common is left in the video processor main body 5 so that it can be used easily by universally compatible use, and the same function can be realized with a small economic burden. Also, by making the adapter part and the video processor part separate,
Function expansion becomes easier than in the case of one.

Next, a first modification of the first embodiment will be described. In the first modification, in addition to the configuration of the first embodiment, as shown in FIG.
In this case, a TV camera mounting scope 64A having a TV camera 63A mounted thereon can be used.

The fiber scope 61 is different from the simultaneous electronic scope 2 A shown in FIG. 2 in that one end face of the image guide 65 is disposed on the focal plane of the objective lens 29, and the formed optical image is provided on the eyepiece section 62 side. Transmit to the end face. The transmitted optical image can be enlarged and observed by the eyepiece 66. The fiberscope 61 is provided with a light guide 26 similarly to the simultaneous electronic scope 2A, and the light guide 26 can be mounted on the light source device 3A.

When the TV camera 63A is mounted on the eyepiece 62, the transmitted optical image is further converted into an image forming lens 67.
The image is formed on the CCD 31 through. This TV camera 63A
In FIG. 1, a single-chip color chip 32 is attached to the front surface of a CCD 31. The CCD 31 photoelectrically converts an optical image color-separated for each pixel by the single-chip color chip 32. A connector 69 is provided at the end of the signal cable 68 extending from the TV camera 63A, and the connector 69 can be connected to the connector receiver 19.

The TV camera mounted scope 64A has the same function as the simultaneous electronic scope 2A. In FIG. 2, a simultaneous camera type scope 70A is used instead of the simultaneous electronic scope 2A. Can be constructed. The components described with reference to FIG. 2 are denoted by the same reference numerals, and description thereof will be omitted. The operation of the first modification is almost the same as that of the first embodiment. Further, according to the first modification, a system configuration for inspection can be selected and used more widely.

In the TV camera 63A of FIG. 7, the single-chip color chip 32 is mounted on the front surface of the CCD 31, so that when the TV camera 63A is mounted on the fiber scope 61, it is similar to the simultaneous electronic scope 2A. Can be used. On the other hand, in the TV camera 63A of FIG.
When the single-chip color chip 32 is not attached to the front surface of the base 31, the same function as that of the surface-sequential electronic scope 2B is provided, and it can be used similarly to the surface-sequential electronic scope 2B.

Next, a second modification of the first embodiment will be described. In the second modification, the light source device is housed in each of the adapters 4A and 4B in the first embodiment. FIG.
As shown in FIG. 2, the light source device 3A shown in FIG. 2 is housed inside the adapter 4A in the case of the simultaneous electronic endoscope system 1A.

In this modification, two contacts a, b of three contacts a, b, c are used instead of the ROM 37A.
Are conducted through the lead wire R. Then, the discrimination circuit 38 detects conduction of the two contacts a and b and outputs a discrimination signal for performing simultaneous signal processing. Other configurations are the same as those in FIG.

The light source device 3B shown in FIG. 3 is housed inside the adapter 4B in the case of the frame sequential electronic endoscope system 1B shown in FIG. In this modification, R
Instead of the OM 37B, for example, two contacts b and c among three contacts a, b and c are electrically connected by the lead wire R. Then, the discrimination circuit 38 detects conduction of the two contacts b and c and outputs a discrimination signal for performing a signal processing in a frame sequential manner. Other configurations are the same as those in FIG.

The lamp 24 may be a xenon lamp, a halogen lamp or a metal halide lamp, or the adapters 4A and 4B may be downsized using high-brightness LEDs. This modification has substantially the same operation and effect as the first embodiment.

FIG. 10 shows a configuration of a main part of an electronic endoscope system 71 according to a second embodiment of the present invention. In the first embodiment, dedicated adapters 4A and 4B corresponding to the simultaneous type electronic scope 2A and the frame sequential type electronic scope 2B, respectively.
This embodiment employs two adapters 4A and 4A.
The electronic endoscope system 71 is formed by using one adapter 4 having the function of B.

The adapter 4 can be detachably attached to the video processor main body 5. The adapter 4 has, for example, a simultaneous drive signal generation circuit 33A and a frame sequential drive signal generation circuit 33B. Adapter 4 is 2
It has two connector receivers 19A and 19B, and each connector receiver 19A and 19B is connected to a connector 18A connected to the simultaneous type electronic scope 2A and a connector 18B connected to the frame sequential type electronic scope 2B, respectively. can do.

A drive signal is applied to the CCD 31 via the connected connector 18A or 18B, and the read CCD output signal is transmitted to the changeover switch S1, the preamplifier 34, the CDS circuit 35, the color separation circuit 36, and the changeover switch S1. To the isolation circuit 44 in the video processor main body 5 via the.

In this embodiment, the connectors 18A and 18B are provided with pins a and b for detecting the scope connection, and are short-circuited by the lead wires R, respectively. Adapter 4
A scope connection detection circuit 72 for detecting the connection of the scope and the type thereof depending on whether any of the pins a and b are short-circuited is housed therein.

When the pins a and b on the connector receiver 19A are short-circuited, the scope connection detection circuit 72 determines that the simultaneous electronic scope 2A is connected and selects a signal processing system corresponding to the simultaneous type. On the other hand, when the pins a and b on the connector receiver 19B side are short-circuited, the field-sequential electronic scope 2
B is determined to be connected, and a signal processing system corresponding to the frame sequential method is selected.

In the case of FIG. 10, since the pins a and b on the connector receiver 19A are short-circuited, the scope connection detecting circuit 72 selects the contact a on the changeover switch S1 and outputs the output of the simultaneous electronic scope 2A. The signal is led to the preamplifier 34, and the changeover switch S2 also selects the contact a side, and the signal passed through the color separation circuit 36 is led to the isolation circuit 44 side.

The scope connection detection signal of the scope connection detection circuit 72 is transmitted to the signal conversion circuit 4 in the video processor body 5.
6 and operates substantially the same as in the first embodiment.
This embodiment has an advantage that the adapter 4 does not need to be replaced. In the second embodiment, a common adapter 4 is used for the simultaneous type and the frame sequential type.

On the other hand, according to the user's selection, FIG.
(A) As shown in FIG. 11 (b), in the case of the simultaneous type and the frame sequential type, dedicated adapters 4A and 4B can be used, respectively, or a common adapter 4 can be used as shown in FIG. May be.

FIG. 11A shows a simultaneous electronic scope 2A.
Is an adapter 4A to be connected, so no scope connection detection is performed. When this adapter 4A is attached to the video processor main body 5, an "L" identification signal can be sent to the video processor main body 5 side. Like that. The signal conversion circuit 46 in the video processor main body 5 uses the "L" identification signal to execute the simultaneous electronic scope 2A.
Is subjected to signal conversion processing.

Similarly, the adapter 4B shown in FIG. 11B does not detect the scope connection, and when the adapter 4B is mounted on the video processor main body 5, an "H" identification signal is sent to the video processor main body 5 side. I can send it. The signal conversion circuit 46 performs a signal conversion process on the frame sequential electronic scope 2B based on the “H” identification signal. Other configurations are the same as those in FIG.

According to this modification, the user has a wider selection range of the system configuration. For example, in the case where only one of the imaging methods is used, FIG.
The system configuration of (b) is suitable. On the other hand, when the two imaging methods are frequently used, the system shown in FIG. 10 which does not require replacement of the adapter 4 is suitable for the two imaging methods.

Next, a third embodiment of the present invention will be described. In this embodiment, an adapter to which an electronic scope is connected is further connected to a video processor main body via a light source device.

In the simultaneous electronic endoscope system 81A according to the third embodiment shown in FIG. 12, a simultaneous electronic scope 82A is used.
Is connected to an adapter 84A, the adapter 84A is connected to a light source device 83A, and the light source device 83A is connected to a video processor main body 85.

At the end of the universal cable 11 of the electronic scope 82A, an integrated connector 86 for the light source and the signal is provided.
A light source & signal connector receiver 87 of FIG. Light guide 26 of electronic scope 82A
Is connected to a light guide connector receiver of the light source device 83A via a light guide 88 in the adapter 84A, and illumination light is supplied to the end face of the light guide 88 from the light source device 83A.

The connector 22 on the back side of the adapter 83A is connected to a comet receptacle 89 on the front face of the light source device 83A, and this comet receptacle 89 is electrically connected to the connector 90 on the back side via a lead wire. The connector 90 has the same shape as the connector 22, and the video processor body 8
5 connector receiver 23.

In this embodiment, for example, two RGB output terminals and two NTSC output terminals are provided. For example, one of the RGB output terminals is connected to the color monitor 6 and the other is connected to a peripheral device 75 such as a printing apparatus. . In addition, the same components as those described in the first embodiment are denoted by the same reference numerals, and description thereof will be omitted.

FIG. 13 shows a frame sequential electronic endoscope system 81B according to the third embodiment. Also in this plane-sequential electronic endoscope system 81B, the plane-sequential electronic scope 82
B is connected to an adapter 84B, the adapter 84B is connected to a light source device 83B, and the light source device 83B
Are connected to the video processor body 85.

The connector 86 of the electronic scope 82B is connected to the connector receiver 87B of the adapter 84B, and the light guide 26 of the electronic scope 82B is connected to the light guide connector receiver of the light source device 83B via the light guide 88 in the adapter 84B. The surface of the light guide 88 is supplied with illumination light in a plane sequence from the light source device 83B.

The connector 22 on the back side of the adapter 83B is connected to a comet receptacle 89 on the front face of the light source device 83B, and this comet receptacle 89 is electrically connected to the connector 90 on the back side via a lead wire. The connector 90 has the same shape as the connector 22, and the video processor body 8
5 connector receiver 23. Other configurations are the same as those described above. In this embodiment, since the connector for the light source and the connector for the signal are integrated, the trouble of attaching and detaching can be reduced. Other effects are almost the same as those of the first embodiment.

Next, a first modification of the third embodiment will be described. In the first modification, when used in a field-sequential electronic scope, a light guide and a color filter disk are housed in a field-sequential adapter to convert white illumination light from a simultaneous light source device into field-sequential illumination light. This is to convert.

In the frame sequential electronic endoscope system 91B shown in FIG. 14, for example, the simultaneous light source device 3A is housed in the video processor main body 95. Light guides 88a and 88b are accommodated in an adapter 92B to which the frame sequential electronic scope 82B is connected, and a color filter disk 57 rotated by a motor 56 is disposed between the light guides 88a and 88b. The white illuminating light from 3A is converted to the illuminating light in a plane-sequential manner.
The light is supplied to the 2B light guide 26. Other configurations are the same as those described above.

In the case of the simultaneous electronic endoscope system, one light guide is arranged in an adapter (not shown), transmits the white illumination light from the light source device 3A, and transmits the light guide of the simultaneous electronic scope 82A. 26. According to this modification, the common parts of the field sequential light source device and the simultaneous type light source device can be shared, so that the cost can be reduced and the field sequential type system and the simultaneous type system are exchanged. In this case, it is possible to save the trouble of replacing and replacing the light source device.

Next, a second modification of the third embodiment will be described with reference to FIG. In the second modification, the light guide 88 in FIG. 11 is provided in the light source device 83A.
Accordingly, in the simultaneous electronic endoscope system 81A ', the connector 86 of the simultaneous electronic scope 82A has the signal connector portion connected to the adapter 84A and the light guide connector portion having the light guide 8 constituting the light source device 83A.
8 is connected.

In the video processor main body 85, N
PAL encoder 5 instead of TSC encoder 51
1 'is used. Other configurations are the same as those in FIG.
The adapter 84A and the video processor main body 85 are connected via an electric wire of the light source device 83A.

Next, a fourth embodiment of the present invention will be described. This embodiment can be used with an electronic scope provided with an autofocus function in the image pickup means. FIG.
Simultaneous electronic endoscope system 1 in the fourth embodiment shown in FIG.
At 01A, in the simultaneous electronic endoscope system 1A shown in FIG. 2, the autofocus actuator 102 is housed at the distal end of the simultaneous electronic scope 2A, so that, for example, the objective lens 29 can be moved back and forth along the optical axis direction. The simultaneous electronic scope 102A is used.

The actuator 102 is connected to the adapter 10
An actuator drive signal is applied from an actuator drive circuit 107 in 4A. The actuator drive circuit 107 is provided in the video processor 1
05, connected to the auto focus control circuit 108,
The objective lens 29 is moved forward or backward along the optical axis according to a control signal from the auto focus control circuit 108. Further, the G signal of, for example, the D / A conversion circuit 47 is input to the auto focus control circuit 108, and focus detection is performed by extracting a high frequency component of the G signal.

FIG. 17 shows an autofocus mechanism. For example, a third lens 29a forming the objective lens 29
Is mounted with a magnet ring 111, and the third lens 29a and the magnet ring 111 are movable in the optical axis direction with respect to the distal end frame 112 to which the remaining objective lens 29 is mounted.

The magnet ring 111 has a spring 113
Urged rearward. An electromagnet 114 is fixed to the end frame 112 so as to face the magnet ring 111, and a triangular wave signal is transmitted from a triangular wave generating circuit 115 constituting the actuator drive circuit 107 via an S / H circuit 116 (and a buffer (not shown)). Is applied.

The triangular wave signal is transmitted to the magnet ring 111
The electromagnet 114 is excited so that the side opposite to the magnet ring has the same polarity, and the magnet ring 1 is repelled according to the signal value.
11 is moved forward. The triangular wave generating circuit 115 outputs a triangular wave signal when an enable signal is applied from the CPU 117 constituting the autofocus control circuit 108.

The auto focus control circuit 108 captures the G signal while the third lens 29a is moving,
The signal component on the high frequency side is extracted via the HPF 118,
The frequency distribution is detected by the FFT 119, the peak frequency that becomes the peak is detected by the peak frequency detection circuit 10, and the peak frequency is transferred to the CPU 117. CPU11
Reference numeral 7 compares the peak frequencies detected in time. When the focus state has the highest peak frequency, that is, the highest spatial frequency, a hold signal is output to the S / H circuit 116 to maintain the objective lens 29 in the focus state.

The other configuration is the same as that of the system 1A shown in FIG. In FIG. 16, the simultaneous electronic scope 102A including the autofocus actuator 102 is connected, but the simultaneous electronic scope 2A shown in FIG. 2 can also be used. When the simultaneous electronic scope 2A is used, the operation is the same as that of the first embodiment. Since the autofocus mechanism is the same in the case of the frame sequential type, the description thereof is omitted.

FIG. 18 illustrates a fifth embodiment of the present invention.
In this embodiment, an electronic scope capable of obtaining, for example, an infrared image as an endoscope image using special light outside the visible region can be used. In the fifth embodiment, the electronic endoscope system 121C when the infrared electronic scope 122C is connected is shown in FIG.
FIG. 18B shows the electronic endoscope system 121A when A is connected. In either case of the electronic scope 122C or 2A, the light source device 3A and the adapter 124A are common (of course, the video processor main body 125 is also common).

The infrared electronic scope 122C is the same as the simultaneous electronic scope 2A, except that an infrared transmission filter 127 is attached to the CCD 31 instead of the single-chip color chip 32. Therefore, an image in the infrared region is formed on the imaging surface of the CCD 31. In the simultaneous electronic scope 2A and the infrared electronic scope 122C, pins a and b for identification are provided in the connector 18 portion.
In A, pins a and b are released, infrared electronic scope 122C
In the figure, pins a and b are short-circuited.

A scope type detection circuit 128 is provided in the adapter 124A, controls the switching of the switches SW1 and SW2 of the adapter 124A according to the detected scope type, and controls the signal conversion circuit 46 in the video processor main body 125. And outputs a control signal suitable for each signal.

For example, when the infrared electronic scope 122C is connected, the contacts SW of the switches SW1 and SW2 are turned on, and a signal of one system is transmitted in the same manner as in the case where the field sequential electronic scope 2B is connected in FIG. Video processor 1
Output to the 25th side. However, unlike the case of the frame sequential type in which three signals are sequentially output in a time series, one signal is sequentially output. In the video processor main body 125, for example, three memories 46 are used in the signal conversion circuit 46.
-1, 46-2, 46-3 simultaneously, monitor 6
Is displayed in black and white (or may be displayed in monochrome using only one memory).

In this embodiment, as shown in FIG. 19, a simultaneous electronic scope provided with an infrared image pickup device is provided.
The infrared electronic scope 122D can also be used. In this case, the electronic scope 122D is provided with a selection switch 129.
By turning ON or OFF the pin 9, the pins a and b can be set to the conductive or released state, and the signal processing of the adapter 124 A and the video processor main body 125 can be selectively set.

It is to be noted that a memory may be further provided in the signal conversion circuit 46 so that one image different in one frame period can be displayed so as to be superimposed on the other image. When the electronic scope 122D shown in FIG.
A visible image and an infrared image can be selectively displayed without exchanging the information.

In the frame sequential imaging method, generally, a visible or
It decomposes into light in the wavelength ranges of the primary colors R, G, and B, and irradiates it sequentially. By irradiating in the ultraviolet and infrared regions for medical and special purposes, information outside the visible range of the human eye is obtained. May be obtained. Infrared observation using infrared rays, that is, measurement of heat distribution, and particularly for medical use, by measuring the distribution of blood oxygen concentration and hemoglobin amount, it is possible to observe lesions at the lower layer below the mucosa.

Therefore, in the case of such a measurement, in the prior art, the R, G, B sequential light is changed to the infrared, R, G, B or infrared,
In contrast to the necessity of sequentially switching to the R, G, and B lights, the present embodiment uses the general-purpose white light source 3A and the normal endoscope image in the visible region without replacing the adapter 124A. An infrared endoscope image is obtained. In the fifth embodiment, an infrared image is obtained. However, an ultraviolet image can be obtained in the same manner by attaching an ultraviolet transmission filter to the CCD. Further, the present invention can be applied to a frame sequential system.

Next, a sixth embodiment of the present invention will be described. In this embodiment, an ultrasonic image is also obtained.
The ultrasonic electronic endoscope system 131E shown in FIG. 20 has, for example, an ultrasonic electronic scope 132E in which an ultrasonic transducer 137 is provided at the tip of a simultaneous electronic scope. The ultrasonic electronic scope 132E has a structure in which an ultrasonic transducer 137 is provided instead of the CCD 31 and the infrared transmission filter 127 in the scope 122D of FIG.

The ultrasonic vibrator 137 includes, for example, a vibrator array in which minute vibrators are two-dimensionally arranged, and a selection circuit (not shown) for selecting a vibrator to be driven. Then, the selection circuit has a structure in which the transducer is sequentially selected in the horizontal direction and the vertical direction, and the drive signal is applied.

This ultrasonic electronic scope 132E is connected to a video processor main body 135 via an adapter 134A. Adapter 134A is adapter 12 shown in FIG.
In addition to the function of 4A, a transducer drive circuit 138 for driving the ultrasonic transducer 137 is provided.

As in the case of the CCD drive signal generation circuit 33A, the oscillator drive circuit 138 receives the synchronization signals HD and V from the synchronization signal generator 42 of the video processor 135.
D is applied via the isolation circuit 43.

The ultrasonic echo signal received by the ultrasonic transducer 137 is inputted to the preamplifier 34 via the contact a of the switch SW1. As in the case of FIG. 19, when the switch 129 is OFF, the contacts b of the two switches SW1 and SW2 are selected, and the state of the signal processing system for the simultaneous electronic scope is established. On the other hand, when the switch 129 is turned on, the two switches SW1 and SW2
Indicates that the contact a is selected and the signal processing system for the ultrasonic scope is in a state. In this state, the same processing as that for the infrared image is performed. In this embodiment, the video processor body 13 is used.
5 can have the same configuration as the video processor body 125 in the case of FIG. Others are the same as those shown in FIG.

In this embodiment, for example, the affected part or the like is endoscopically inspected as a simultaneous electronic scope, and when more detailed information on the affected part is desired, the distal end is brought into contact with the affected part and the switch 129 is turned on, so that the affected part is Ultrasonic waves are emitted to the side.

The echo from the portion where the acoustic impedance changes at the affected part is received by the ultrasonic transducer 137, converted into an electric signal to become an echo signal, and subjected to the same signal processing as in the case of the infrared CCD. An ultrasonic image is displayed on the monitor 6. According to this embodiment, since acoustic image information can be obtained in addition to optical image information, it is possible to provide inspection means more suitable for making a diagnosis. Note that an ultrasonic image may be displayed together with an endoscopic image as in a modification of the sixth embodiment shown in FIG.

The ultrasonic electronic endoscope system 1 shown in FIG.
51E has, for example, an ultrasonic electronic scope 152E in which an ultrasonic vibrator 157 is provided at the tip of a simultaneous electronic scope. This ultrasonic electronic scope 152E has an adapter 154.
A is connected to the video processor main unit 155 via A.
The adapter 154A has a function of the adapter 4A shown in FIG. 2, a vibrator drive circuit 158 for driving the ultrasonic vibrator 157, and an echo signal amplifying circuit for amplifying the ultrasonic echo signal received by the ultrasonic vibrator 157. 159 are stored.

As in the CCD drive signal generation circuit 33A, the oscillator drive circuit 158 includes synchronization signals HD and V from the synchronization signal generator 42 of the video processor 155.
D is applied via the isolation circuit 43.

The ultrasonic echo signal amplified by the echo signal amplifying circuit 159 is input to an echo signal processing circuit 160 in the video processor main body 155, converted into a video signal, and then converted into an output signal of the contour emphasizing circuit 48 and the like. The ultrasonic image added by the adder 161 can be displayed on the monitor 6. Other configurations are almost the same as those of the system shown in FIG.

FIG. 22 shows an electronic endoscope system 161 according to the seventh embodiment of the present invention. In this embodiment, an adapter is not directly connected to the video processor but is connected via a cable.

In the system 1 shown in FIG. 1, the video processor main body 5 has a recess 2 in which the adapter 4A or 4B can be stored.
The electronic endoscope system 161 is provided with a connector receiver 167 provided on the front surface of the video processor main body 165 and a connector 22 provided on the back surface of the adapter 4A or 4B.
Are connected by a cable 170 provided with connectors 168 and 169 at both ends. Others are the same as the first embodiment.

FIG. 23 shows a simultaneous electronic endoscope system 181A according to the eighth embodiment of the present invention. This embodiment corresponds to imaging means having different numbers of pixels. Also,
The isolation circuit is provided not on the video processor main body but on the adapter.

Simultaneous electronic scopes 182A, 182
A 'has CCDs 31 and 31' having different numbers of pixels, and signal connectors 187 of the electronic scopes 182A and 182A '.
187 'is provided with identification signal generating means for indicating that the scopes have different numbers of pixels. In this embodiment, for example, the CCD 31 'has four times the number of pixels (for example, twice the number of pixels in the vertical direction and twice the number of pixels in the horizontal direction) of the CCD 31, and the identification signal generating means includes pins a and b, for example.
Can be distinguished from those that have been released and those that have been short-circuited.

Scope type discrimination for discriminating (detecting) which electronic scope 182I (I = A or A ') by discriminating whether pins a and b are open or short-circuited in adapter 184A. A circuit 188 is provided, and the detected signal is output to the video processor main body 185 and the drive signal generating circuit 3
3A is applied to the control terminals of the vertical and horizontal transfer signals.

The drive signal generation circuit 33A outputs vertical and horizontal transfer signals for reading out four times the number of pixels in the case of the CCD 31 'according to the "H" or "L" level of the output signal of the scope type determination circuit 188. . Specifically, the vertical and horizontal transfer signals φV & φH shown in FIG.
In the case of 31 ', it is output for four times the period.

In the signal conversion circuit 46, according to the output signal of the scope type discrimination circuit 188, in the case of the CCD 31 ', it is four times as large as the CCD 31 (twice in the vertical direction,
(2 times in the horizontal direction). Therefore, as shown in FIG. 24, in the case of the CCD 31 ', an image area 6a' which is four times the image area 6a of the CCD 31 is displayed on the monitor 6.

Further, in this embodiment, the isolation circuits 43 and 44 are provided not in the video processor main body 185 but in the video processor main body 185.
It is provided in the adapter 184A. In this case, when the adapter 184A is connected to the video processor main body 185, the housing chassis of the adapter 184A can be electrically connected to the secondary circuit housing chassis in the video processor main body 185. In this case, the GND terminal of each circuit in the adapter 184A (the GND terminal of the patient circuit).
Is suspended from the housing chassis of the adapter 184A.

When the isolation circuits 43 and 44 are provided in the video processor main body 185, the adapter 184 is used.
Since the housing chassis on the A side is electrically connected to the GND of the patient circuit, the housing chassis needs to be insulated from the housing chassis on the video processor main body 185 side. Although this embodiment has been described by using the simultaneous method, the present invention can also be applied to a frame sequential method.

In this embodiment, for the sake of simplicity, the number of one pixel is four times the number of one pixel. However, the signal conversion circuit 46 may be provided with an interpolation circuit or an image enlargement or reduction circuit. You may make it possible to cope with the case of other multiples. Further, an electronic endoscope system that can handle different numbers of pixels as shown in FIG. 25 may be configured.

This system shows a configuration in which the number of pixels of the CCD 244 provided on the electronic scope 241 is different.

In this system, for example, for 30,000 pixels, 10
Scope compatible unit 242 for 10,000 pixels and 200,000 pixels
Is prepared. CCD 24 in electronic scope 241
Scope compatible unit 2 according to the number of pixels of 4
Reference numeral 42 is connected to the processor main body 243.

The scope corresponding unit 242 is provided with a ROM 245 for generating characteristic information such as pixel information indicating the number of pixels of the CCD corresponding to this unit. Type and characteristics, ie, electronic scope 24
The number of pixels of the CCD 244 in 1 is determined.

The processor main body 243 is provided with three clock signal generators 246, 247, and 248 for generating clock signals corresponding to the number of pixels of the CCD, and the clock signals generated by these generators are provided. Are supplied to the synchronizing signal generation circuit 23 via the switch circuit 249. Three clock signal generators 24
6,247,248 are provided for 30,000 pixels, 100,000 pixels, and 200,000 pixels, for example. The selection of the clock signal in the switch circuit 249 is performed by the determination circuit 25.
Is switched by a selection signal based on the result of the determination.

In general, under the same image output size condition that the output video signal has the same screen size, if the number of pixels of the CCD 244 is different, it is necessary to switch the driving frequency of the CCD 244 according to the number of pixels. In this embodiment, the driving frequency of the CCD driving signal is switched by selecting different clock signals from the three clock signal generators 246, 247, and 248.

When the scope corresponding unit 242 is connected to the processor main body 243, the number of pixels of the CCD 244 is determined by the determination circuit 25 based on the characteristic information from the ROM 245, and the input of the switch circuit 249 is switched according to the determination result. Three clock signal generators 246, 2
A clock signal generator corresponding to the number of pixels of the CCD is selected from 47 and 248. A clock signal output from the selected generator is input to a synchronization signal generation circuit 223, and a horizontal transfer drive signal and a vertical transfer drive signal for the CCD 244 are generated using the clock signal as a source signal.

Synchronization signals such as the horizontal transfer drive signal and the vertical transfer drive signal are input to the CCD drive circuit 218, and the CCD 244 is optimally driven by the CCD drive signal output from the CCD drive circuit 218 having a drive frequency suitable for the number of pixels. Is driven.

A control signal is also input to the video signal processing circuit 224 and the like based on the determination result of the determination circuit 225, the operation mode is switched, and the photoelectric conversion output of the CCD 244 is optimally subjected to video signal processing, so that the TV monitor 232 And the peripheral device 233.

As described above, the scope-compatible unit suitable for the number of pixels of the CCD is connected to the processor body, and the clock signal generator is selected in accordance with the unit to switch the drive frequency of the CCD drive signal, thereby minimizing the drive frequency. By switching the circuits, it is possible to handle a plurality of types of electronic scopes equipped with CCDs with different numbers of pixels.
The size can be reduced.

FIG. 26 shows a configuration of an electronic endoscope system which can support two imaging systems, that is, a simultaneous system and a frame sequential system.
In the simultaneous system and the frame sequential system, each system has advantages and disadvantages, and is selectively used depending on the field of the observation target site. In this system, the scope compatible unit 252 has two CCDs, one for the simultaneous mode and the other for the frame sequential mode.
Driving circuits 256 and 257 are provided to support a plurality of imaging methods.

In this embodiment, for a specific CCD, that is, a CCD having the same number of pixels, two methods of the simultaneous method and the frame sequential method are used.
It corresponds to one imaging method. Therefore, according to the number of pixels of the CCD 255 in the electronic scope 251, a suitable scope-compatible unit 252 is
53. Further, a light source device 254 corresponding to an imaging method is connected to the electronic scope 251.

The scope corresponding unit 252 is provided with a CCD drive circuit 256 for the frame sequential method and a CCD drive circuit 257 for the simultaneous method. The outputs of the two drive circuits are input to the switch circuit 258. The switch circuit 258 selects a CCD drive signal according to the imaging method. Further, a ROM 260 for generating characteristic information possessed by the scope corresponding unit 252 is provided, and the type of the scope corresponding unit 252 is determined by the determination circuit 25 of the processor main body 253.

The processor main body 253 is provided with a ROM 261 storing characteristic information for determining whether the processor main body 253 is for the simultaneous system or the frame sequential system. Input to the switch circuit 258 of the
Switch circuit 2 so that the output of the CD drive circuit is selected.
58 is switched.

When the scope corresponding unit 252 is connected to the processor main body 253, the number of pixels of the CCD 255 is determined by the determination circuit 225 based on the characteristic information from the ROM 260, and the synchronization signal generation circuit 22 is determined according to the determination result.
3. The operation mode of the video signal processing circuit 224 and the like is switched. Further, based on the characteristic information from the ROM 261 of the processor main body 253, the input of the switch circuit 258 is switched so as to be compatible with the imaging method of the processor main body 253, and the CCD from the CCD driving circuit 256 or 257 is switched.
The drive signal is selected.

At this time, the CCD driving circuits 256 and 25
In 7, a synchronization signal is input from the synchronization signal generation circuit 223, and a CCD drive signal corresponding to each imaging method is generated. The selected CCD drive signal is supplied to the CCD 255 of the electronic scope 251, and the CCD 255 is driven in an optimal state.

That is, the scope corresponding unit 252
The output of the circuit is selected so as to be optimal in combination with the processor main body 253. In addition, CCD2
The 55 photoelectric conversion output is input to the video signal processing circuit 224 via the CDS circuit 219, where the video signal processing is performed, and the processed video signal is transmitted to the TV monitor 232 and the peripheral device 233.

If the processor itself is provided with functions corresponding to the simultaneous system and the frame sequential system, there are problems such as an increase in the number of signal processing circuits and an increase in cost. As described above, the processor main body 253 and the scope-compatible unit 252 are separately detachable, and the minimum circuit switching is performed by selecting the CCD drive signal output from the scope-compatible unit 252 according to the imaging method. Can support a plurality of imaging methods.

FIG. 27 shows a system for changing the display area according to the number of pixels of the CCD of the electronic scope. According to the number of pixels of the CCD 274 in the electronic scope 271, a suitable scope corresponding unit 272 is connected to the processor main body 273.

The scope-compatible unit 272 is provided with a ROM 275 for generating characteristic information such as pixel information indicating the number of pixels of the CCD corresponding to this unit. The type and characteristics, that is, the number of pixels of the CCD 274 in the electronic scope 271 are determined.

The processor main body 273 is provided with mask signal generators 276 and 277 for setting the screen size of the output video signal according to the number of pixels of the CCD.
This mask signal is a signal for deleting (masking) a signal corresponding to the peripheral portion of the output screen to set an output screen product. The mask signal generator 276 is a mask signal for a large-size output screen. And the mask signal generator 277 outputs a mask signal for a small-sized image output screen.

The mask signals generated by the mask signal generators 276 and 277 are supplied to the video signal processing circuit 24 via the switch circuit 278. The selection of the mask signal in the switch circuit 278 is performed by the determination circuit 2
Switching is performed by a selection signal based on the determination result of No. 5. Here, for example, if the number of pixels of the CCD is 3
In the case of 10,000 pixels, the mask signal for the small-sized output screen is
When the number of pixels is 200,000, a mask signal for a large-sized image output screen is selected.

In general, in an electronic endoscope apparatus, the output screen area on a TV monitor is changed according to the number of pixels of an image sensor. In other words, when the number of pixels of the image sensor is small, the image is deteriorated when the image is displayed on the entire screen of the monitor. About 1/4.

When the scope corresponding unit 272 is connected to the processor main body 273, the number of pixels of the CCD 274 is determined by the determination circuit 25 based on the characteristic information from the ROM 275, and the input of the switch circuit 278 is switched according to the determination result. The output of one of the mask signal generators corresponding to the number of pixels of the CCD is selected from the mask signal generators 276 and 277. The mask signal output from the selected generator is input to the video signal processing circuit 224, and the size of the screen displayed on the TV monitor 32 is determined according to the mask signal.

The video signal processing circuit 224 is provided with a video mixer circuit. The video signal processing circuit 224 removes an unnecessary signal area on the periphery of an output screen of the video signal by the gate means based on the mask signal. ing. That is, by mixing the video signal and the mask signal during the video signal processing, unnecessary signal areas of the video signal are deleted,
Monitor 23 of a video signal output according to the number of pixels
The output screen area at 2 is changed.

At this time, a control signal is also input to the video signal processing circuit 224 and the like based on the determination result of the determination circuit 225, the operation mode is switched, and the photoelectric conversion output of the CCD 274 is optimally subjected to video signal processing.

In the TV monitor 232, as shown in FIG. 28, the subject image is displayed on the display screen 232a of the monitor. When the number of pixels of the CCD 274 is 200,000 by the above-described masking process, FIG. When the number of pixels is 30,000, an output screen 279b with a small output area is displayed as shown in FIG. 28 (b).

As described above, the scope-compatible unit suitable for the number of pixels of the CCD is connected to the processor main body, and the mask signal is switched according to the number of pixels of the CCD of the electronic scope. When connecting various kinds of electronic scopes, the output screen on the monitor can be changed so as to have an optimal size for the number of pixels by switching the circuits with a minimum.

The above-described embodiments can be partially combined with each other to form different embodiments, which also belong to the present invention.

[0151]

As described above, according to the present invention, by mounting a dedicated adapter corresponding to the imaging system on the processor body, it is possible to easily cope with imaging probes of different imaging systems, Cost can be reduced.

[Brief description of the drawings]

FIG. 1 is an overall configuration diagram of an electronic endoscope system according to a first embodiment of the present invention.

FIG. 2 is a block diagram showing a configuration of a simultaneous electronic endoscope system.

FIG. 3 is a block diagram showing a configuration of a frame sequential type electronic endoscope system.

FIG. 4 is a block diagram illustrating a configuration of a signal conversion circuit.

FIG. 5 is a configuration diagram of a light source device of a frame sequential type.

FIG. 6 is an explanatory diagram showing output signals of a drive signal generation circuit.

FIG. 7 is a block diagram showing a configuration of a simultaneous endoscope system according to a first modification of the first embodiment;

FIG. 8 is a block diagram showing a main part of the configuration of a simultaneous electronic endoscope system according to a second modification of the first embodiment;

FIG. 9 is a block diagram showing a main part of the configuration of a frame sequential electronic endoscope system according to a second modification of the first embodiment.

FIG. 10 is a configuration diagram of a main part of an electronic endoscope system according to a second embodiment of the present invention.

FIG. 11 is a configuration diagram showing main parts of a field sequential type and simultaneous type electronic endoscope system according to a modification of the second embodiment.

FIG. 12 is a block diagram showing a configuration of a simultaneous electronic endoscope system according to a third embodiment of the present invention.

FIG. 13 is a block diagram illustrating a configuration of a field sequential electronic endoscope system according to a third embodiment.

FIG. 14 is a block diagram showing a configuration of a field sequential electronic endoscope system according to a first modification of the third embodiment.

FIG. 15 is a block diagram showing a configuration of a simultaneous electronic endoscope system according to a second modification of the third embodiment.

FIG. 16 is a configuration diagram of a simultaneous electronic endoscope system according to a fourth embodiment of the present invention.

FIG. 17 is an explanatory diagram of an autofocus mechanism.

FIG. 18 is a configuration diagram showing main parts of an infrared and simultaneous electronic endoscope system according to a fifth embodiment of the present invention.

FIG. 19 is a configuration diagram showing a main part of an electronic endoscope system for infrared and visible.

FIG. 20 is a configuration diagram showing a main part of an ultrasonic electronic endoscope system according to a sixth embodiment of the present invention.

FIG. 21 is a configuration diagram showing an ultrasonic electronic endoscope system according to a modification of the sixth embodiment.

FIG. 22 is an overall configuration diagram of an electronic endoscope system according to a seventh embodiment of the present invention.

FIG. 23 is a configuration diagram showing a simultaneous electronic endoscope system according to an eighth embodiment of the present invention.

FIG. 24 is an explanatory diagram showing that the display size of an endoscope image on a monitor is different.

FIG. 25 is an overall configuration diagram of a simultaneous electronic endoscope system.

FIG. 26 is an overall configuration diagram of a simultaneous electronic endoscope system in a modification of FIG. 25;

FIG. 27 is an overall configuration diagram of a simultaneous electronic endoscope system.

FIG. 28 is an explanatory view showing an image output screen of the TV monitor.

[Explanation of symbols]

 DESCRIPTION OF SYMBOLS 1 ... Electronic endoscope system 2A, 2B ... Electronic scope 3A, 3B ... Light source device 4A, 4B ... Adapter 5 ... Video processor main body 6 ... Color monitor 7 ... VTR 8 ... Insertion part 9 ... Operation part 11 ... Universal cable 12, 18, 22 ... connector 13 ... tip 14 ... curved part 19, 23 ... connector receiver 21 ... recess 24 ... lamp 26 ... light guide 28 ... subject 29 ... objective lens 31 ... CCD 32 ... single plate color chip 33A, 33B ... CCD Drive signal generation circuit 35 CDS circuit 36 Color separation circuit 37A, 37B ROM 38 Discrimination circuit 42 Synchronization signal generation circuit 43, 44 Isolation circuit 46 Signal conversion circuit 48 Outline enhancement circuit 51 Encoder

──────────────────────────────────────────────────続 き Continued on front page (58) Field surveyed (Int.Cl. ⁷ , DB name) A61B 1/00-1/32

Claims (1)

(57) [Claims] A first probe having an elongated first insertion portion, a first imaging means provided on a distal end side of the first insertion portion, and taking an image of an object; 2 is provided on the distal end side of the second insertion portion, and the second imaging portion is different from the first imaging means in the imaging method .
A second probe unit having an imaging unit, a first adapter unit connected to the first probe via a cable, and generating a drive signal compatible with an imaging method of the first imaging unit; A second adapter unit that is connected to the second probe via a cable, generates a drive signal that is compatible with the imaging method of the second imaging unit, and is separate from the first adapter unit; A first and second adapter unit having a connection portion to be selectively detachably connected, wherein the first and second adapter units are connected to each other;
For generating the drive signal to be supplied to the imaging means.
A main unit that sends out a synchronization signal and performs a signal process suitable for the first and second imaging units to generate a standard video signal; and is connected to the main unit to display the video signal. An imaging system comprising: a monitor;