JPH06189900A - Electronic endoscopic device - Google Patents

Abstract

PURPOSE:To provide an electronic endoscope device which decreases isolation parts to the utmost, can enhance safety and can be miniaturized. CONSTITUTION:Plural pulse generators 16, 22, 25 supply the timing necessary for subjecting the signal obtd. from a CCD 8 to processing. The output of the CCD 8 is supplied via the isolation 18 to an extraction circuit 23 and a signal processing circuit. This extraction circuit 23 extracts the reset pulses superposed on the output of the CCD 8. The extracted reset pulses are supplied to the plural pulse generators 22, 25 to reset the internal circuits, by which the synchronization with the pulse generator 16 is obtd.

Description

Detailed Description of the Invention

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to an improvement in an electronic endoscope system for synchronizing a plurality of pulse generators.

[0002]

2. Description of the Related Art In recent years, by inserting an elongated insertion portion into a body cavity, it is possible to observe internal organs in the body cavity and, if necessary, perform various medical treatments using a treatment instrument inserted in a treatment instrument channel. Endoscope (scope or fiberscope)
Is widely used. Further, it is used not only for medical purposes but also for industrial purposes for observing and inspecting objects in pipes of machines such as boilers, machines and chemical plants or machines.

Further, various electronic endoscopes of the type in which a solid-state image pickup device such as a charge-coupled device (CCD) is used as an image pickup means and image information is taken out as an electric signal photoelectrically converted are also used.

An electronic endoscope apparatus using the electronic endoscope as a medical device, for example, connects a circuit unit (patient side circuit) for connecting a circuit or the like to be inserted into a body cavity of a patient with peripheral devices such as a monitor. The circuit part (secondary side circuit) to be operated must be insulated. Therefore, the video signal processing circuit for processing the electric signal of the solid-state imaging device is provided with the isolation circuit in order to insulate the patient circuit side from the secondary circuit side. This is a measure for preventing electric shock of the patient and ensuring safety.

The electric signal photoelectrically converted by the solid-state image pickup device is input to a patient side circuit of a video signal processing circuit via a cable, is pre-processed, and is then input to a secondary side circuit via an isolation circuit. To be done. Then, the electric signal is post-processed and further output to a peripheral device such as a monitor (not shown).

Japanese Unexamined Patent Publication (Kokai) No. 3-114432 proposes an electronic endoscope apparatus in which even if noise is mixed in the synchronizing signal, the noise does not disturb the image signal. This electronic endoscope apparatus has a plurality of pulse generators that generate a timing clock. The plurality of pulse generators are provided in the patient side circuit and the secondary side circuit, respectively. The two circuit systems are synchronously coupled by using a PLL circuit, and the pulse generator on the secondary side receives the horizontal and vertical synchronization signals from the pulse generator on the patient side via two isolations. , Are supposed to be in sync.

In the secondary-side pulse generator, the secondary-side (synchronized circuit system) or patient-side (synchronous circuit system) reset signal selected according to the detection result of the phase locked state of the PLL circuit is used. , It is supposed to synchronize.

In Japanese Patent Laid-Open No. 3-114432, a horizontal synchronizing signal (H
D) and a vertical sync signal (VD) are required. The entire device has three isolation sections in combination with the video signal isolation circuit.

However, the greater the number of isolation parts, the higher the possibility that the insulation will be broken due to a failure or the like. In addition, the number of isolation elements increases, the device cannot be downsized, and there is room for improvement.

Further, when synchronizing a plurality of pulse generators, the amount of delay due to the transmission cable and isolation has not been taken into consideration. For this reason, the CCD output is delayed with respect to the synchronization signal, and when digital processing is performed, the pixel is displaced from one to several clocks with respect to the synchronization signal, and there is room for improvement.

[0011]

As described above, in the conventional example, two types of synchronizing signals, that is, a horizontal synchronizing signal (HD) and a vertical synchronizing signal (VD) are required for synchronizing the patient side and the secondary side. I am trying. In addition, the entire apparatus is provided with three isolation sections together with the video signal isolation circuit.

The more isolation sections there are, the more
There is a high possibility that insulation will be destroyed due to a failure or the like. Further, when the number of isolation parts increases, the device cannot be downsized and there is room for improvement.

The present invention has been made in view of the above circumstances, and it is an object of the present invention to provide an electronic endoscope apparatus in which the number of isolation portions is reduced as much as possible, and safety can be improved and downsized.

[0014]

According to the present invention, there are provided a plurality of timing generation means for supplying timings required for processing a signal obtained from an image pickup means, and a timing supplied by the plurality of timing generation means. , Reset signal generating means for generating a reset signal for resetting all.

[0015]

[Operation] According to the configuration of the present invention, all the timing generating means are reset by the reset signal generated by the reset signal generating means.

[0016]

Embodiments of the present invention will be described below with reference to the drawings. 1 is a block diagram of an electronic endoscope apparatus according to a first embodiment of the present invention.

The electronic endoscope apparatus 1 shown in FIG. 1 is an electronic endoscope 2 for picking up an image of a subject and outputting an electric signal, and an electric signal from the electronic endoscope 2 is subjected to various necessary processes to produce an image. A signal processing device 3 that outputs a signal and a synchronization signal, and a light source device 4 that supplies illumination light to the subject via the endoscope 2 are provided.

The endoscope 2 has a light distribution lens 5 at the tip of the insertion portion, and a light guide 6 at the rear end of the light distribution lens 5.
The emission end of is arranged. Illumination light from the light source device 4 is incident on the incident end of the light guide 6. Further, in the endoscope 2, an objective optical system 7 is arranged at the tip of the insertion portion, and a CCD 8 as an image pickup means is arranged at the rear end of the objective optical system 7. A color filter (not shown) is arranged on the image pickup surface of the CCD 8.
In this color filter, filters that respectively transmit a plurality of colors are arranged in a mosaic pattern.

Further, the light source device 4 emits white (illumination) light, and a condenser lens 10 for condensing the light emitted by the light source lamp 9 and supplying it to the incident end of the light guide 6. And have.

The object illuminated by the illumination light is imaged on the image pickup surface of the CCD 8 by the objective optical system 7, and is color-separated by the color filter. That is, the CCD 8 photoelectrically converts the subject image into an electric signal and outputs the electric signal based on the simultaneous system.

The CCD 8 of the endoscope 2 and the signal processing device 3 are electrically connected by a cable 11.

The CCD 8 is the CCD of the signal processing device 3.
The drive pulse of the driver 14 is received via the cable 11 and driven. The signal processing device 3 inputs the electric signal of the CCD 8 that is driven and read out through the cable 11 and outputs the signal to a circuit in the subsequent stage through isolation or the like described later. That is, the signal processing device 3 has a patient side circuit and a secondary side circuit connected to the endoscope 2 as will be described later, and the patient side circuit and the secondary side circuit are isolated for patient safety. Has been set up.

The signal processing device 3 has a CCD driver 14 for supplying the CCD 8 with a reset pulse to be superimposed on the output of the CCD 8 and a CCD drive pulse. The pulse output from the CCD driver 14 is supplied to the CCD 8 via the cable 11 and drives the CCD 8.

Further, the signal processing device 3 receives a first clock oscillator 15 for generating a clock and a pulse for generating a reset pulse and a CCD drive pulse in the CCD driver 14 in response to the clock. A first pulse generator 16 for generating and supplying.

The electric signal read out from the CCD 8 is transmitted via the cable 11 to the first cable length detection circuit 1
It is designed to enter 7. The first cable length detection circuit 17 detects the cable length from the output signal of the CCD 8, while the CCD driver 14 adjusts the crest value of the drive waveform, matching, etc. according to the detected length. Has become. The first cable length detection circuit 17 detects the cable length from the amount of attenuation of the output of the CCD 8, for example. Alternatively, the detection circuit 17
Is the pulse supplied by the CCD driver 14 and the CCD 8
The cable length is detected based on the phase difference between the pulses output by. The cable length detection circuit 17 is not limited to the above example.

The electrical signal output from the CCD 8 is input to the isolation amplifier 18 via the cable 11. isolation·
Amplifier (hereinafter abbreviated as isolation) 18
Isolates the patient side circuit in the front (input) stage and the secondary side circuit in the rear (output) stage. The isolation 18 may be, for example, an element such as a photocoupler or a transformer, as long as it can transmit the output signal of the CCD 8 and can sufficiently maintain the withstand voltage required between the patient side and the secondary side. It is not particularly limited. Further, in particular, it may not have the amplification function.

The output stage of the isolation 18 is connected to a second cable length detection circuit 19 and a correlated double sampling circuit (hereinafter abbreviated as CDS) 20. The second cable length detection circuit 19 detects the cable length from the output signal of the isolation 18 and supplies the detected output to the voltage controlled oscillator 21. The voltage controlled oscillator 21 oscillates a clock according to the detection output, that is, a cable length is corrected.

The clock oscillated by the voltage controlled oscillator 21 is supplied to the second pulse generator 22 as timing generating means and the CDS 20. In the CDS 20, the output of the isolation 18 is sampled by this clock to obtain an electric signal of the CCD 8 from which noise is removed.

The output of the CDS 20 is supplied to the reset pulse extraction circuit 23 and the A / D converter 24.

The reset pulse extraction circuit 23 extracts the reset pulse superimposed on the CCD output in the patient side circuit from the CDS output.
The reset pulse extraction circuit 23 uses the second pulse generator 2
2, and the extracted reset pulse is supplied to the third pulse generator 25 as the timing generating means.

The second pulse generator 22 receives the first pulse from the reset pulse and the cable length-corrected clock.
The signal processing pulse and the memory write control pulse are generated. Hereinafter, the first signal processing pulse is abbreviated as the first processing pulse. The write control pulse of the memory will be abbreviated as a write pulse hereinafter.

The output signal of the CDS 20 is converted into a digital signal by the A / D converter 24.
The digital signal from the A / D converter 24 is the first
In the signal processing circuit 26, AGC (auto gain control), brightness / color processing, white balance, γ correction, etc. are performed. The first signal processing circuit 2
Reference numeral 6 denotes the timing of the first processing pulse for performing the various processing.

The signal, which has been subjected to various processes in the first signal processing circuit 26, is written in the memory 27. Memory 2
The write timing in 7 is controlled by the write pulse.

On the other hand, in the third pulse generator 25,
The following pulse is generated from the clock generated by the second clock oscillator 28 and the reset pulse extracted from the CDS output. That is, the third pulse generator 25 generates a memory read control pulse and a second signal processing pulse. Hereinafter, the memory read control pulse is abbreviated as a read pulse. The second signal processing pulse will be abbreviated as the second processing pulse hereinafter.

Data is read from the memory 27 at the timing of the read pulse. The signal read from the memory 27 is supplied to the second signal processing circuit 29.

The read signal from the memory 27 is processed by the second signal processing circuit 29 such as correction, contour enhancement and encoding. Second signal processing circuit 29
The signal that has been subjected to various kinds of processing in 1 is converted into an analog signal in the D / A converter 30 and output as a video signal. The video signal is supplied to the outside through the video output terminal 31.

Further, the synchronizing signal is supplied from the third pulse generator 25 to the outside through the synchronizing signal output terminal 32.

In the above configuration, the first pulse generator 16 receives the clock generated by the first clock oscillator 15 and generates a predetermined pulse. CC receiving this pulse
The D driver 14 generates a CCD drive pulse and a reset pulse to be superimposed on the output of the CCD 8.

The CCD driver 14 sends a CCD drive pulse and a reset pulse to the C line via the cable 11.
Supply to CD8. In the CCD 8, reading is performed by the CCD drive pulse, and a reset pulse is superimposed on the read electrical signal.

The output signal of the CCD 8 is the cable 11
And is supplied to the first cable length detection circuit 19 via. The first cable length detection circuit 19 detects the cable length and adjusts the peak value, matching, etc. of the output waveform of the CCD driver 14 according to the length. Therefore, the CCD driver 14 corrects the attenuation of the CCD output due to the cable length, and uses a pulse having a proper waveform with matching C
CD8 can be driven reliably. Further, the reset pulse superimposed on the CCD 8 can be similarly corrected, and a signal having an appropriate waveform can be sent to the isolation 18.

The patient side circuit and the secondary side circuit are isolated by an isolation 18.
The second cable length detection circuit 19 has isolation 1
The output signal of 8 detects the influence of the isolation and the cable length on the secondary side, and the detection output controls the voltage controlled oscillator 21. From the voltage controlled oscillator 21, a clock whose cable length has been corrected is obtained.
This clock is used by the second pulse generator 25 and the CDS2.
It is being supplied to 0.

The CDS 20 double-samples the output of the isolation 18 with a clock having a stable waveform to obtain a noise-free baseband output.

On the other hand, the reset pulse extraction circuit 23 has a C
The reset pulse superimposed on the output of the CCD 8 is extracted from the output of the DS 20 and supplied to the second pulse generator 23 and the third pulse generator 25.

The second pulse generator 22 generates a first signal processing pulse and a write pulse from the extracted reset pulse and the clock whose cable length has been corrected.

The output of the CDS 20 is the A / D converter 2
4 is converted into a digital signal, and the first signal processing circuit 26
Are subjected to AGC control, brightness / color processing, white balance, γ correction, etc., and written in the memory 27.

On the other hand, in the third pulse generator 25, the second pulse
The read pulse and the second processing pulse are generated from the clock generated by the clock oscillator 28 and the extracted reset pulse.

Here, the pulses generated by the second pulse generator 22 and the third pulse generator 25 are synchronized by a reset pulse at a constant cycle. That is, the second and third pulse generators 22 and 25 are
The phase of the pulse generated by the first pulse generator 22 is matched at a predetermined timing.

The signal read from the memory 27 by the read pulse is subjected to processing such as color correction, edge enhancement and encoding in the second signal processing circuit 29. Then, the signal after various processing in the second signal processing circuit 29 is
It is converted into an analog signal by the D / A converter 30 and output as a video signal.

In this embodiment, a plurality of pulse generators are provided, and the reset pulse generated by one pulse generator of the patient side circuit resets the other pulse generators, and the reset pulse is output to the CCD output. It was made to overlap. Therefore, in the apparatus of this embodiment, it is not necessary to transfer a plurality of signals in order to synchronize a plurality of pulse generators. Therefore, in this embodiment, only one isolation is required, the separation between the patient side and the secondary side becomes more complete, and the safety can be improved.

Further, in the present embodiment, the number of parts such as isolation is reduced, so that miniaturization can be realized. As described above, the device according to the present embodiment can reduce the number of isolation parts between the patient side and the secondary side, further improve the safety as a medical device, and reduce the size.

Further, in this embodiment, since the plurality of pulse generators are synchronized only by the reset pulse (for example, frame reset) and the writing / reading of the memory is made independent, the CCD output and the video output can be obtained. There is no need to adjust the horizontal rate with. Therefore, in this embodiment, CC
The driving speed of D can be freely determined, and
A CD can be driven at a low speed, a CCD with a low pixel can be driven at a high speed, and processing such as reading a plurality of times can be easily realized. This can increase the resolution of the image, for example.

Further, FIG. 2 shows a modified example in which the first embodiment is applied to an apparatus of a frame sequential imaging system.

The electronic endoscope device 33 shown in FIG. 2 has a light source device 34 in place of the light source device 4 of the first embodiment. The light source device 34 supplies color plane sequential illumination light to the light guide 6. The light source device 34 is
On the optical path between the light source lamp 9 and the condenser lens 10, a rotary filter 35 having three optical color filters R (red), G (green), and B (blue) arranged at equal intervals on the circumference is arranged. I am doing it. The rotary filter 35 is rotated at a predetermined rotation speed by a motor 36.

The light source device 34 includes a rotary filter 35.
It has a rotary filter phase detector 37 for detecting the phase of the rotation. The phase detection result is supplied to the second pulse generator 22A via the phase detection signal input terminal 39. The second pulse generator 22A as the timing generation means is adapted to generate a drive timing pulse for the rotary filter 35 of the light source in addition to the function of the second pulse generator 22. The drive timing pulse is supplied to the rotary filter drive circuit 38 via the timing pulse output terminal 40.

The rotation filter drive circuit 38 of the light source device 34 controls the rotation of the motor 36 by the pulse output from the second pulse generator 22A.

In addition, the same components and operations as those of the first embodiment are designated by the same reference numerals, and the description thereof will be omitted.

With the above structure, the second pulse generator 22A
Generates a drive timing pulse based on the phase detection result of the rotary filter 37. At this time, the second pulse generator 22A is reset at a predetermined timing by the extracted reset pulse. Then, the rotary filter 37 rotates in synchronization with the drive timing pulse.

On the other hand, the first signal processing circuit 26 performs signal processing at the timing of the first signal processing pulse generated by the second pulse generator 22A. As a result, in the present modification, the color frame of the color plane sequential illumination light can be synchronized with the readout of the CCD and the processing in the first signal processing circuit 26.

This modification is an application of the first embodiment to an electronic endoscope of the image-sequential imaging system, and other configurations and effects are the same as those of the first embodiment, and the description thereof will be omitted.

FIG. 3 is a block diagram of an electronic endoscope apparatus according to the second embodiment of the present invention. The second embodiment will be described below with reference to FIG.

The apparatus 41 of the second embodiment has an external synchronization signal input terminal 42 in order to enable external synchronization with the first embodiment.
And a pulse extraction circuit 43 is added.

The second reset pulse extraction circuit 43
Is for extracting an external reset pulse from the external synchronization signal supplied from the external synchronization signal input terminal 42.
This external reset pulse may be supplied from the reset pulse extraction circuit 23 of the device shown in FIG. 1, for example.

The external reset pulse is supplied to the first pulse generator 16 through the second isolation 44 separating the secondary side and the patient side. In the first pulse generator 16, the internal circuit is reset in response to this external reset pulse. Furthermore, a reset pulse to be superimposed on the CCD output is also generated. Other configurations and operations similar to those of the first embodiment are designated by the same reference numerals and description thereof will be omitted.

As described above, in this embodiment, since the external resetting is possible, the external synchronization is also possible, and the same operation and effect as those of the first embodiment are obtained.

FIG. 4 shows a first modified example in which the second embodiment of the present invention is applied to an apparatus of the frame sequential imaging system.

The electronic endoscope device 43 shown in FIG. 4 has a light source device 34 similar to that shown in FIG. 2 in place of the light source device 4 of the second embodiment. The electronic endoscope device 43 has a second
In place of the pulse generator 22 of No. 2, the second pulse generator 22A same as the modification shown in FIG. 2 is provided.

The phase comparison circuit 45 provided in the secondary side circuit includes an external rotary filter phase pulse input terminal 46.
A phase detection pulse is input via the.

The phase comparison circuit 45 compares the phases of the external phase detection pulse and the internal phase detection pulse of the rotary filter phase detector 37. The second
The pulse generator 22A controls the rotary filter drive timing pulse based on the comparison result, thereby enabling the external synchronization of the rotary filter 35.

That is, the first modification is applied to the electronic endoscope apparatus of the frame-sequential imaging system, and the same effect as the second embodiment can be obtained. The rest of the configuration, functions and effects are the same as those of the second embodiment, and the explanation is omitted.

FIG. 5 is a block diagram according to a second modification of the second embodiment shown in FIG. Device 4 of the second modified example
In the seventh modification, the second reset pulse extraction circuit 43 extracts the reset pulse from the internal rotation filter phase generation pulse and operates it. Therefore, the external synchronization signal input terminal 42 shown in FIG. 4 is unnecessary. The other configurations, functions and effects are the same as those of the first modified example, and a description thereof will be omitted.

FIG. 6 is a block diagram according to a third modification of the second embodiment shown in FIG.

The apparatus 50 of the third modification shown in FIG. 6 is different from that of the second embodiment in the clock supply source of the third pulse generator 25. The clock supplied to the third pulse generator 25A of the third modified example is a pulse obtained by inputting a pulse obtained from the external synchronization signal via the PLL loop.

Phase lock pulse extraction circuit 5 shown in FIG.
Reference numeral 1 is for extracting a horizontal synchronizing signal or a color subcarrier pulse from the synchronizing signal input through the external same-signal input terminal 42. Phase lock pulse extraction circuit 51
The pulse extracted by is compared with the output of the second voltage controlled oscillator 52 by the phase comparator 52. The second voltage controlled oscillator 53 controlled by the phase comparator 52 constitutes a PLL,
A clock is supplied to the third pulse generator 25A.

In addition to the function of the third pulse generator 25, the third pulse generator 25A supplies the clock supplied thereto to a not shown concord circuit of the second signal processing circuit 29, etc. It is also possible to synchronize the phase of the color subcarrier of the composite video output with the outside.

The rest of the configuration, operation and effect are the same as those of the second embodiment, and the explanation is omitted.

FIG. 7 is a block diagram of an electronic endoscope apparatus according to the third embodiment of the present invention. The third embodiment will be described below with reference to FIG.

The device 55 of the third embodiment is a configuration example in which the reset pulse is sent without being superimposed on the CCD output in the first embodiment. Other configurations and operations similar to those of the first embodiment are designated by the same reference numerals and description thereof will be omitted.

The phase of the reset pulse generated by the first pulse generator 16 is controlled by the variable delay circuit 56 according to the cable length detected by the first cable length detection circuit 17. The reset pulse with phase adjustment is
Second isolation 4 separating the patient side and the secondary side
4 to the second pulse generator 22B and the third pulse generator 22B. Second pulse generator 22
B and the third pulse generator 22B correspond to the second pulse generator shown in FIG.
The pulse generator 22 and the third pulse generator 22 have the same function.

Other than that, the same components and operations as those of the first embodiment are designated by the same reference numerals, and the description thereof will be omitted.

In this embodiment, the phase of the reset pulse generated by the first pulse generator 16 is controlled according to the cable length. Therefore, in this embodiment, a stable reset operation can be performed even if the scope length changes. In addition, the same effect as the first embodiment can be expected in the present embodiment.

FIG. 8 is a block diagram of an electronic endoscope apparatus according to a modification of the third embodiment. The electronic endoscope device 60 shown in FIG. 8 has an example of a configuration that enables external synchronization.

The second reset pulse extraction circuit 43
Extracts an external reset pulse from the external synchronization signal input from the external synchronization signal input terminal 42 and supplies it to the second pulse generator 22C.

The second pulse generator 22C resets its internal circuit and generates a reset pulse in response to an external reset pulse.

The reset pulse generated by the second pulse generator 22C is supplied to the third pulse generator 25A and the variable delay circuit 61. The variable delay circuit 61
Then, the phase of the reset pulse is controlled according to the cable length detected by the second cable length detection circuit 19, and the patient is passed through the second isolation 44 that separates the secondary side and the patient side. Side first pulse generator 16
Supply to.

The second pulse generator 22C has the same function as the second pulse generator 22.

The other operation is the same as that of the third modification shown in FIG.

Although the external reset pulse is input to the second pulse generator 22C, the third pulse generator 25A
May be input to the first pulse generator 16 or may be input to the first pulse generator 16 via isolation.

Furthermore, this embodiment is based on FIG. 2, FIG. 4 and FIG.
It can also be applied to a frame-sequential type electronic endoscope like the device shown in FIG.

The external signal input to the external sync signal input terminal 42 may be a composite sync signal, a horizontal sync signal and a vertical sync signal, or a sync signal which is an integral multiple of the vertical sync signal.

The systems shown in FIGS. 9 to 14 respectively show examples in which the present invention is applied to a configuration example in which a plurality of electronic endoscope apparatuses and the like are connected.

FIG. 9 is a schematic configuration diagram of a system according to the fourth embodiment of the present invention.

The system shown in FIG. 9 has a plurality of electronic endoscope devices 71, 72, ..., 73. The electronic endoscope devices 71, 72, ..., 73 each include an endoscope, a signal processing device, and a light source device. A video signal is output from each signal processing device, and a monitor, a printer, and a VT are provided, respectively.
It is connected to equipment such as R. From the signal processing device of the electronic endoscope device 71, for example, a synchronization signal including a reset pulse is output and input to the signal processing devices of the other devices 72, ..., 73.

In the present embodiment, in a plurality of electronic endoscope apparatuses, the reset pulse output from one location enables synchronization for signal processing in all other apparatuses.

The endoscope may be a single-plate (simultaneous) type electronic endoscope or a frame-sequential type electronic endoscope.
Alternatively, a mixture of them may be used. Further, the electronic endoscope apparatus can be configured by appropriately applying the apparatus shown in FIGS. 1 to 8.

The system shown in FIG. 10 is a schematic configuration diagram according to a first modification of the fourth embodiment. In the first modified example,
Instead of the electronic endoscope device 71, an ultrasonic diagnostic device 74 having an ultrasonic endoscope 81 as an image pickup means is combined. A reset pulse is supplied from the ultrasonic diagnostic signal processing device of the ultrasonic diagnostic device 74 to another signal processing device.

The ultrasonic diagnostic apparatus 74 is not limited to one set, and a plurality of ultrasonic diagnostic apparatuses 74 may be provided. Other configurations and effects
Since it is similar to the fourth embodiment, the description is omitted.

The system shown in FIG. 11 is a schematic configuration diagram according to a second modification of the fourth embodiment. In the second modified example,
Instead of the electronic endoscope device 71, a combination with a patient monitoring camera device 75 having a patient monitoring camera 82 as an image pickup means is also possible. It is also possible to combine with other video equipment.

From the patient monitoring camera signal processing device of the patient monitoring camera device 75, a reset pulse is supplied to another signal processing device. The patient monitoring camera device 75 is not limited to one set, and a plurality of patient monitoring camera devices 75 may be provided.
The rest of the configuration, functions and effects are the same as those of the fourth embodiment, and the explanation is omitted.

FIGS. 12, 13, and 14 are schematic configuration diagrams respectively relating to the third, fourth, and fifth modifications of the fourth embodiment.

The system shown in FIG. 12 is the system shown in FIG. 9 in which the respective video outputs are combined so that they can be displayed on a monitor, printed out by a printer, or recorded by a VTR or the like. Therefore, the synthesizing / switching device 76 inputs the respective video signals, synthesizes the respective signals, or switches them by a selector or the like and outputs them to each terminal device.

The system shown in FIG. 13 is a modification of the system shown in FIG. 10, and the system shown in FIG. 14 is a modification of the system shown in FIG. Reference numeral 77,
Reference numerals 78 are combining / switching devices.

As described above, by using the electronic endoscope apparatus of the present invention, it is possible to freely synchronize with other video equipment.

Further, by using another device capable of external synchronization, the electronic endoscope of the present invention can be freely combined and mixed.

[0104]

As described above, according to the present invention, all the timing generating means are reset by the reset signal generated by the reset signal generating means.
It is not necessary to transfer a plurality of signals in order to synchronize a plurality of timing generation means, so that the isolation part between the patient side and the secondary side is reduced, and the safety and the size are further improved. The effect is that you can.

[Brief description of drawings]

FIG. 1 is a block diagram of a single plate type electronic endoscope apparatus according to a first embodiment.

FIG. 2 is a block diagram of a frame sequential electronic endoscope apparatus according to a modification.

FIG. 3 is a block diagram of a single plate type electronic endoscope apparatus according to a second embodiment.

FIG. 4 is a block diagram of a frame sequential electronic endoscope apparatus according to a first modification.

FIG. 5 is a block diagram of a frame sequential electronic endoscope apparatus according to a second modification.

FIG. 6 is a block diagram of a single-plate electronic endoscope device according to a third modification.

FIG. 7 is a block diagram of a single plate type electronic endoscope apparatus according to a third embodiment.

FIG. 8 is a block diagram of a single-plate electronic endoscope device according to a modification.

FIG. 9 is a connection diagram between devices according to the fourth embodiment.

FIG. 10 is a connection diagram between devices according to a first modification.

FIG. 11 is a connection diagram between devices according to a second modification.

FIG. 12 is a connection diagram between devices according to a third modification.

FIG. 13 is a connection diagram between devices according to a fourth modification.

FIG. 14 is a connection diagram between devices according to a fifth modification.

[Explanation of symbols]

 DESCRIPTION OF SYMBOLS 1 ... Electronic endoscope device 2 ... Endoscope 3 ... Signal processing device 4 ... Light source device 14 ... CCD driver 15 ... First clock oscillator 16 ... First pulse generator 21 ... Voltage controlled oscillator 22 ... Second Pulse generator 23 ... Reset pulse extraction circuit 28 ... Second clock oscillator 25 ... Third pulse generator 17, 19 ... Cable length detection circuit

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[Procedure amendment]

[Submission date] May 25, 1993

[Procedure Amendment 1]

[Document name to be amended] Statement

[Correction target item name] 0040

[Correction method] Change

[Correction content]

The output signal of the CCD 8 is the cable 11
And is supplied to the first cable length detection circuit 19 via. First
The No. 1 cable length detection circuit 17 detects the cable length and adjusts the peak value, matching, etc. of the output waveform of the CCD driver 14 according to the length. Therefore, the CCD driver 14 corrects the attenuation of the CCD output due to the cable length, and uses a pulse having a proper waveform with matching C
CD8 can be driven reliably. Further, the reset pulse superimposed on the CCD 8 can be similarly corrected, and a signal having an appropriate waveform can be sent to the isolation 18.

[Procedure Amendment 2]

[Document name to be amended] Statement

[Correction target item name] 0041

[Correction method] Change

[Correction content]

The patient side circuit and the secondary side circuit are isolated by an isolation 18.
The second cable length detection circuit 19 has isolation 1
The output signal of 8 detects the influence of the isolation and the cable length on the secondary side, and the detection output controls the voltage controlled oscillator 21. From the voltage controlled oscillator 21, a clock whose cable length has been corrected is obtained.
This clock is used by the second pulse generator 22 and the CDS2.
It is being supplied to 0.

[Procedure 3]

[Document name to be amended] Statement

[Correction target item name] 0043

[Correction method] Change

[Correction content]

On the other hand, the reset pulse extraction circuit 23 has a C
A reset pulse superimposed on the output of the CCD 8 is extracted from the output of the DS 20 and supplied to the second pulse generator 22 and the third pulse generator 25.

[Procedure amendment 4]

[Document name to be amended] Statement

[Correction target item name] 0047

[Correction method] Change

[Correction content]

Here, the pulses generated by the second pulse generator 22 and the third pulse generator 25 are synchronized by a reset pulse at a constant cycle. That is, the second and third pulse generators 22 and 25 are
The phase of the pulse generated by the first pulse generator 16 is matched at a predetermined timing.

[Procedure Amendment 5]

[Document name to be amended] Statement

[Correction target item name] 0074

[Correction method] Change

[Correction content]

In addition to the function of the third pulse generator 25, the third pulse generator 25A uses the supplied clock to encode the second signal processing circuit 29 (not shown).
It is also possible to synchronize the phase of the color subcarrier of the composite video output to the outside by supplying it to a circuit or the like.

[Procedure correction 6]

[Document name to be amended] Statement

[Correction target item name] 0078

[Correction method] Change

[Correction content]

The phase of the reset pulse generated by the first pulse generator 16 is controlled by the variable delay circuit 56 according to the cable length detected by the first cable length detection circuit 17. The reset pulse with phase adjustment is
Second isolation 4 separating the patient side and the secondary side
4 through the second pulse generator 22B and the third pulse generator
Supplied to the generator 25B . Second pulse generator 22
B and the third pulse generator 25B are the second pulse generator shown in FIG.
Of the pulse generator 22 and the third pulse generator 25 of FIG.

[Procedure Amendment 7]

[Document name to be corrected] Drawing

[Name of item to be corrected] Figure 7

[Correction method] Change

[Correction content]

[Figure 7]

Claims (1)

[Claims] 1. A plurality of timing generation means for supplying timings necessary for processing a signal obtained from an imaging means, and a reset signal for resetting all the timings supplied by the plurality of timing generation means. An electronic endoscope apparatus comprising: