JPH02249527A - Electronic endoscope device - Google Patents

Abstract

PURPOSE:To automatically detect a king of a source so as to set the scope in an optimum condition by controlling at least one of a drive means and a signal process means with the use of a consumption current detecting means for detecting a consumption current of an image pick-up so as to discriminate a kind of the image pick-up means. CONSTITUTION:When an endoscope 2 having a consumption current I1 is connected to a control device 4, a switch 3 is closed so as to energize a differential circuit 39. Meanwhile, illumination light delivered from a light source lamp 33 is irradiated to an incident end surface of a light guide 31 through a focusing lens 36, and is irradiated to a subjective part by a light distributing lens system 22. An image of the illuminated subjective part is formed on an image pick-up surface of a solid image pick-up element 23 by an objective lens system 21, and is then photo-electrically converted. Drive clock pulses generated from a drive clock generating circuit 37 is compensated by a drive waveform compensating circuit 26, corresponding to a signal wire 28 from the endoscope 2, and the then delivered to the solid image pick-up element 23, so as to read an image signal which is then delivered to a monitor 6 so as to be displayed as an endoscope image.

Description

[Detailed description of the invention] [Industrial application field] The present invention relates to an electronic endoscope having a solid-state image sensor.

[Prior art and problems to be solved by the invention] In recent years, organs within a body cavity can be observed by inserting an elongated insertion part into a body cavity, and if necessary, it can be inserted into a neck 11 channel. Endoscopes that can perform various therapeutic procedures using treatment tools are widely used.

Furthermore, various electronic endoscope devices using a solid-state image sensor, such as a COD, at the tip have been proposed.

FIG. 11 shows the overall configuration of the electronic endoscope.

In the figure, an electronic endoscope device 1 includes an endoscope 2, a light source device 3 that supplies illumination light to the endoscope 2, and a control device 4 that controls the endoscope 2 and has a signal processing section. , and a monitor 6 that displays endoscopic images. The endoscope 2 has an operating section 8 connected to the rear of an elongated insertion section 7, and the insertion section 7 is provided with a distal end section 9, a curved section 11, and a flexible section 12 from the distal end side. There is.

The operating section 8 is provided with a bending operation knob 13 for bending the bending section 11.

These electronic endoscope devices are broadly classified into bronchial, upper gastrointestinal, and lower gastrointestinal tracts depending on the internal organs to be observed.
Each endoscope has a different length and diameter. In addition, since endoscopes are used by being inserted into body cavities, the outer diameter of the tip is thinner and the rigid section is shorter, which is a particularly important factor because the observation range is wider and the operability is improved. There is.

Here, the difference in scope length means that the length of the drive signal transmission cable for the built-in solid-state imaging device also differs. In addition, as mentioned above, because a scope is required to be thin and have a short rigid section, the number of components mounted on the tip of the scope is limited to a minimum. No matching (termination) is performed. In other words, when the scope lengths are different, it is necessary to switch the correction of the transmission waveform on the main body processing device side.

As a technique to solve this problem, Japanese Patent Application Laid-Open No. 62-54215
The publication number is shown. To explain this technology in FIG. 12, the switching circuit 19 detects whether the electrical contact 18 provided on the scope connector 16 is open or short-circuited, and switches the drive signal to the solid-state image sensor, for example. , for optimization.

Furthermore, in Japanese Patent Publication No. 63-47453, a resistor for the model contact is provided on the inner chain side, thereby generating a reference voltage,
A technique for controlling light rl on the light source side has been proposed.

However, in conventional systems that determine the type of scope based on the combination of mechanical connections between the scope connector and the main processing unit, it is necessary to increase the number of contacts on the connector, which is a problem for users. There was room for improvement in terms of ease of insertion and removal, that is, increased strength.

The present invention has been made in view of the above circumstances, and provides operability that automatically detects the scope type and sets the optimum conditions without increasing the minimum number of contacts of the connector. The purpose is to provide a good electronic endoscope.

[Means and effects for solving the problems] The electronic endoscope device of the present invention includes an imaging means having a solid-state imaging device that converts a subject image into an electrical signal, and a drive signal that outputs a drive signal to the imaging means to convert the solid-state imaging device into an electrical signal. a driving means for driving and outputting an image signal; a signal processing means for processing the image signal output from the means 111 and converting it into a video image; and displaying a subject image in response to the image signal from the signal processing means. Current consumption detection means for determining the type of imaging means by detecting the current consumption of the display means and the imaging means, and changing the setting of at least one of the driving conditions of the driving means and the signal processing conditions of the signal processing means. It is equipped with the following.

In the present invention, the solid-state imaging device is driven by the driving means to output an image signal, and this image signal 23 is processed by the signal processing means, and an endoscopic image is displayed by the display means. At least one of the drive means and the signal processing means is controlled by a current consumption detection means that determines the type of the imaging means by detecting the current consumption of the R image means,
This is considered to be the optimum driving condition or signal processing condition.

[Example] Hereinafter, the present invention will be specifically explained with reference to the drawings.

1 and 2 relate to a first embodiment of the present invention, and FIG. 1 is a block diagram illustrating the overall configuration of an electronic endoscope device;
FIG. 2 is a circuit diagram of the drive waveform correction circuit and the current consumption detection circuit.

In this embodiment, the same components as those in the prior art shown in FIG. 11 are given the same reference numerals, and the explanation thereof will be omitted.

In this embodiment, the waveform distortion of the drive clock is compensated for by determining the type of endoscope, that is, the distance of the signal line from the control device to the solid-state image sensor.

An objective lens system 21 and a light distribution lens system 22 are provided at the distal end portion 9 of the endoscope 2 as an imaging means constituting the electronic endoscope device 1 of this embodiment. A solid-state image sensor 23 is provided at the rear so that its imaging surface is at the imaging position of the objective lens 21. This solid-state image sensor 23 is inserted through the insertion section 7, the operation section 8, the universal cord 29, and the SCOB connector 16, and is connected to the control device @4 by signal lines 28, 28, . ... is connected to a video signal processing circuit 24 as a signal processing means provided in the control unit device 4, a drive waveform correction circuit 26 as a drive means, and a consumption current detection circuit 27 as a consumption current detection means. .

Further, behind the light distribution lens system 22, an output end face of a light guide 31 that transmits illumination light is disposed. The light guide 31 is inserted through the insertion section 7, the operation section 8, the universal cord 29, the scope connector 16, and the light source cord 32, and is detachably connected to the light source device 3. The light source device 3 includes a light source lamp 3 that outputs illumination light.
3, a rotary filter 34 serving as a color separation filter that sequentially separates the illumination light output from the light source lamp 33 into, for example, red (R), green (G), and blue (B) color light; and this rotary filter. A condensing lens 36 is provided which condenses the colored light transmitted through the light guide 34 and irradiates it onto the input Q4 end face of the light guide 31.

The control device 4 is provided with a drive clock generation circuit 37, and the generated drive clock is input to the drive waveform correction circuit 26. Further, the consumption upstream detection circuit 27 internally monitors and monitors the power from the power supply circuit 38.
I2, the consumed current is detected, the scope length of the endoscope 2, that is, the length of the signal line 28 is determined, and a control signal is output to the drive waveform correction circuit 26. Further, the video signal processing circuit 24 outputs the video A signal obtained by signal processing to a monitor 6 serving as a display means to display an endoscopic image.

The drive waveform correction circuit 26 and the current consumption detection circuit 27 are constructed as shown in FIG.

The drive waveform correction circuit 26 is a differentiating circuit 39.40.4 composed of a variable capacitor and a variable resistor for waveform correction.
1, and the drive clock from the drive clock generation circuit 37 is inputted to each drive clock. The drive clocks whose waveforms have been corrected by the differentiating circuits 39, 40, and 41 are outputted to the solid-state image pickup device 23 through switches 43, 44, and 45, respectively. Switch 43, 44.45
One of them is closed by a control signal from the current consumption detection circuit 27.

In the current consumption detection circuit 27, a power supply circuit 38 is connected to one end of the low resistance R1, and three comparators 46, 4
Connected to the non-inverting input terminal of 7.48. The other end of the resistor R1 is connected to the solid-state imaging cable 23 and also to one end of the resistor R2. The other end of the resistor R2 is connected to the inverting input end of the comparator 46 and also to one end of the resistor R3.

The other end of the resistor R3 is connected to the inverting input terminal of the comparator 47 and also to one end of the resistor R4.

The other end of the resistor R4 is connected to the inverting input end of the comparator 48 and also to one end of the resistor R5.
The other end is grounded.

The output terminal of the comparator 46 is an AND gate 50°51.
52 input terminal. The output terminal of the comparator 47 is connected to the input terminals of AND gates 51 and 52, and is also connected to the input terminal of an AND gate 50 via an inverter 53. The output terminal of comparator 48 is AND
It is connected to the input end of gate 52 and, via an inverter 54, to the input ends of AND gates 50 and 51, respectively.

The output end of the AND gate 50 is connected to the switch 43, the output end of the AND gate 51 is connected to the switch 44, and the output end of the AND gate 52 is connected to the switch 43.
The protruding horn ends are each connected to a switch 45.

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

When the scope connector 6 is connected to the control device 4, the current consumption detection circuit 27 detects the current consumption of the endoscope 2.

In this embodiment, three scales R2 are connected to the control device 4, and the current consumption of these endoscopes 2 is set to 11. Let I2°I3.

When the endoscope 2 with a current consumption of 11 is connected to the W control device M4, and power is supplied from the power supply circuit 38, the low resistance R1 connected in series has a current of 21
A potential drop of =11xRl occurs, and this voltage E1 is supplied to comparators 46, 47°48. Reference voltage et of comparator 46, 47, 48, e2. e3 is set as follows between potential drops E1, E2, and E3 obtained across the low resistance R1 in each of the three types of endoscopes 2.

el<<62 <<e3 El <<E2 <<E3 el<El , e2 <E2 , e3 <E3 The applied voltage E1 is greater than el and smaller than e2°e3. In this case, the outputs and AND outputs of the respective comparators 46, 47, and 48 are as shown in Table 1 below.

In addition, the switch 43 (the first switch 43 sets the differential circuit 39 as a waveform compensation circuit to V for the connected endoscope 2) performs waveform correction suitable for the endoscope 2.

Below, current consumption 12. When J3 endoscope is connected,
The control signal from the current consumption detection circuit 27, that is, AND
The signals from gates 50.51.52 are as shown in Table 2.

Table 2 As described above, only the output of the AND gate 50 becomes "1", and the consumption type fi! is connected to this AND gate 50 as described above. When the endoscope 2 of t I 1 is connected, the switch 43 is closed and the differentiating circuit 39 reduces the current consumption I
When an endoscope 2 with a current consumption of I3 is connected, the switch 44 is closed and the differential circuit 40 is activated. When an endoscope 2 with a current consumption of I3 is connected, the switch 45 is closed and the differential circuit 41 is activated. are in the operating state.

On the other hand, the illumination light output from the light source lamp 33 of the light source device 3 is converted into R and G by a rotating filter 34.

The B color light is sequentially separated into each color light and is irradiated onto the incident end surface of the light guide 31 by the condenser lens 36. The illumination light transmitted through the light guide 31 is irradiated onto the subject part by the light distribution lens system 22. An image of the illuminated object part is formed on the imaging surface of the solid-state image sensor 23 by the objective lens system 21, and is photoelectrically converted. The drive clock generated by the drive clock generation circuit 37 is corrected by the drive waveform correction circuit 26 in accordance with the signal q1i) 28 of the endoscope 2, and then sent to the solid-state image sensor 23. Read out the signal. The read image signal is processed by the video signal processing circuit.
After processing such as separation of G and 83 primary color signals, γ correction, enhancement, etc., the R, G, and B signals are encoded and output to the monitor 6 as a luminance signal Y and chroma signal C or NTSC signal and displayed as an endoscopic image. .

As described above, according to this embodiment, since the current consumption of the endoscope 2 is detected, there is no need to provide an electrical contact for detection in the connector part, although it is possible to detect a plurality of internal signals #ft2. , the operability can be improved.

Figures 3 to 5 relate to the second embodiment of the present invention;
FIG. 4 is a block diagram showing the main parts of the second embodiment, FIG. 4 is a circuit diagram of the control limiting circuit, and FIG. 5 is a control characteristic diagram of the gain control amplifier.

Kinotake has an automatic gain control circuit that electrically increases the gain of the output signal of the solid-state image sensor and keeps the level constant when the reflected light from the subject decreases and observation is difficult. This is an application of the present invention.

In this embodiment, the setting value of the control @ range setting circuit of the automatic gain control circuit having a feedback loop is changed to switch the gain up level that is optimal for the S/N of each endoscope or the solid-state image sensor used. .

In FIG. 3, the image signal ') from the solid-state image sensor 23 is input to a gain control amplifier 56.The output of this gain control amplifier 56 is input to the video signal processing circuit 24 and is integrated by an integration circuit 57. is input to the inverting input terminal of the comparator 58. A variable resistor R6 is connected to the non-inverting input terminal of the comparator 58, and the signal input to the inverting input terminal is connected to the reference level set by the variable resistor R6. The output of the comparator 58 is connected to a control limiting circuit 59, and for example, when the signal level is higher than the reference level, it becomes L level, and when it is lower, it becomes H level.

The control restriction circuit 59 will be explained using FIG. 4.

The output of the comparator 58 is connected to the gain control amplifier 56 via a resistor R7 and to switches 62, 63, 64 via a diode 61. The switch 62 is connected to the current detection circuit 2 described in the first embodiment.
It opens and closes in response to a control signal A from 7, and is in a closed state when an endoscope 2 with a current consumption of 11 is connected, and in other cases, is in an open state. Further, the switch 63 is opened and closed in response to a control signal, and is in a closed state when the endoscope 2 with a current consumption of I2 is connected, and in other cases, is in an open state.

Furthermore, the switch 64 is opened and closed by the control signal C.

It is in an open state when the endoscope 2 with a current consumption of 3 is connected, and in other cases, it is in an open state.

The switch 62 is connected to the reference potential e1, the switch 63 to the base Fv-potential e2, and the switch 64 to the reference potential e3.

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

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

When the endoscope 2 with a current consumption of 11 is connected to the control device 4,
The current detection circuit 27 is an AN current detection circuit 27 as described in the first embodiment.
outputting a control signal from the D gate 50 to the switch 62;
This switch 62 is opened.

The image signal from the solid-state image sensor 23 of the connected endoscope 2 is input to the video signal processing circuit 24 via the gain control amplifier 56, and is also input to the integrating circuit 57 where it is integrated. For example, the signal level integrated over one field is input to the comparator 58 and compared with the U level set by the variable resistor R6. Here, when there is little reflected light from the subject, the signal level becomes low and the output of the comparator 58 becomes H level. Further, in normal brightness observation, the output of the comparator 58 is at L level. As a result, a control signal equal to the reference potential e3 is input to the gain control amplifier 56 in the case of the H level, and a control signal output from the comparator 58 is input to the gain control amplifier 56 in the case of the L level. The gain control amplifier 56 has characteristics as shown in FIG. 5, electrically gains up the image signal output from the solid-state image sensor 23, and outputs it to the video signal processing circuit 24.

Erase the following in the same way! ! ? If an endoscope 2 with a current of 12.13 is connected and the image becomes dark, the reference potential e1. A control signal with a signal level equal to e2 is input to the gain control amplifier 56, and the fifth
The gain is increased as shown in the figure.

According to this embodiment, even when a plurality of endoscopes are connected, optimal gain adjustment is performed.

Other effects are similar to those of the first embodiment.

FIG. 6 is an explanatory diagram of the current consumption detection means according to the third embodiment of the present invention.

In this embodiment, a low resistance is connected to the power supply line to the endoscope in the first embodiment, but this potential drop does not occur.

In FIG. 6(a), the sensor section 66 is a trochoidal core 67 made of a ferromagnetic material such as a circular ferrite core, and a thin conductive wire 69 is wound around the core 67.
A power supply line 68 to the endoscope 2 is inserted through the inside. A magnetic field component is detected from the current flowing through this power supply line 68 and converted into a voltage.

The conductive wire 69 is connected to the comparator 46 described in the first embodiment.
．． 47 and 48, the connected endoscope 2 is determined.

In this embodiment, one end of the resistor that generates the reference voltage of the comparator is grounded, and one end of the sensor section 66 may also be grounded for operation.

Other configurations, operations, and effects are the same as those in the first embodiment.

FIG. 6(b) shows a modification of FIG. 6(a),
A conductive wire 69 is wound around a square core 70, and the basic operation and effects are the same.

FIG. 7 is a schematic circuit diagram of an endoscope according to a fourth embodiment of the present invention.

Each of the above embodiments is suitable when the current consumption within the endoscope differs depending on the endoscope, for example when solid-state image sensors with different numbers of pixels are used, but this embodiment It can also be used in endoscopes for the bronchus, upper gastrointestinal tract, lower gastrointestinal tract, etc., which use a solid-state image sensor and have the same configuration as other circuits within the endoscope.

This embodiment can be adapted to any internal configuration.

The current consumption inside the endoscope is generally determined by the solid-state image sensor and the buffer amplifier for transmitting the output signal, and the same type of solid-state image sensor has approximately the same value. Therefore, a unit resistor RJ is added between the power supply line and GND, thereby making it possible to set a difference in the current consumption between the narrow rod type scopes.

A solid-state detection element 23 is provided at the tip of the endoscope 2, and this solid-state image sensor 23 has a power supply line 71 and a signal line 7 that transmits signals read out from the solid-state image sensor 23.
2, a drive signal line 73 that drives the solid-state image sensor 23,
A GND line 74 is connected. A buffer amplifier 76 is connected to the signal line 72. The power supply line 71, the signal line 72, the drive signal line 73, and the GND line 74 are inserted up to the scope connector 16. By connecting this scope connector 16 to the control device 4, the power supply line 71 and GND line 74 are connected to the current consumption detection circuit 27, the signal line 72 is connected to the video signal processing circuit 24, and the drive signal line 73 is connected to the drive waveform correction circuit 26. are connected to each other. Inside the scope connector 16, the power supply line 71 and the GND line 74 are connected to a resistor Rρ.
connected by. The resistance value of this resistor R1 is determined depending on the endoscope, so that the current consumption detection circuit 27 can detect the current consumption corresponding to the endoscope 2.

This resistor R1 may be mounted inside the scope connector 16, and its size, heat generation, etc. do not matter.

On the other hand, even if the types of endoscopes increase, the detection circuit can be handled by simply adding a comparator and an AND gate.

FIG. 8 is a block diagram illustrating the overall configuration of an electronic endoscope device according to a fifth embodiment of the present invention.

In this embodiment, the drive waveform correction circuit 26 described in the first embodiment
and the gain control amplifier 56 provided in the video signal processing circuit 24 described in the second embodiment are controlled by the power consumption detection circuit 27.

The configuration of this embodiment is similar to the first and second embodiments.

By configuring as in this embodiment, one control device 4 can connect a plurality of endoscopes 2 with different signal line lengths.
Moreover, even if the brightness of the image decreases, gain control suitable for the connected family celebration vA2 can be performed.

Therefore, the operability of the electronic endoscope device can be improved.

FIG. 9 is an explanatory diagram of an electronic endoscope device according to a sixth embodiment of the present invention.

In the first to fourth embodiments described above, an electronic internal 81 mirror having a solid-state image pickup device at its tip was described, but in this embodiment, an external TV camera is attached to the eyepiece of a fiberscope.

The endoscope device 81 of this embodiment includes a rigid endoscope 82, a fiberscope 83, an external TV camera 84 that can be detachably attached to the rigid endoscope 82 and the fiberscope 83, and a fourth Control device 4 and monitor 6 described in the embodiment
It is made up of.

The rigid endoscope 82 is provided with an operating section 87 at the rear of a rigid insertion section 86, and an eyepiece section 88 at the rear end of the operating section 87.

The fiberscope 83 is provided with an operating section 91 at the rear of a flexible insertion section 89, and an eyepiece section 92 is provided on this operating section 91. A universal cord 93 extends from the side of the operating section 91 and is connected to a light source device (not shown).

The external TV camera 84 is detachably attached to the eyepiece section 88, 92.

This external TV camera 84 is composed of an adapter section 96 having an imaging optical system 94, a moire removal filter 97, and a camera head main body 98 having a solid-state image sensor 23, and an adapter section 96 that extends from the camera head main body 98. The signal cable 99 is connected to the control device 4.

The control device 4 has the configuration described in the fourth embodiment, and can connect a plurality of external TV cameras 84 with different signal line markings. Gain control suitable for the attached TV camera 84 can be performed.

Other configurations, operations, and effects are the same as those of the fourth embodiment.

FIG. 10 is an overall explanatory diagram of an endoscope apparatus according to a seventh embodiment of the present invention.

In the first and fifth embodiments, an endoscope device using a frame-sequential imaging method was described, but in this embodiment, in addition to the frame-sequential imaging method, an electronic endoscope using a color mosaic imaging method and an external TV
An endoscope device having a camera will be described.

In this embodiment, a field-sequential electronic endoscope 101A and a color mosaic electronic endoscope 101A are used. JAt! t101B and screen sequential TV
A fiber scope with a camera 101C, a fiber scope with a color mosaic TV camera 101D, a fiber scope 101E, and a frame sequential video processor 10
2A, a color mosaic video processor 102B, a light source device 103, and a monitor 6.

A universal cord 104 extends from each of the electronic endoscopes 101A, 101B and the fiber scopes 101C, 101D, 101E, and a light source connector 106A, 106B is attached to the tip of the universal cord 104.
, 106G, 106D, and 106E are provided.

Signal cables 107A and 107B are further extended from the light source connectors 106A and 106B, and a signal connector 108A is attached to the ends of these cables 107A and 107B.
, 108B are provided. In addition, the field sequential type T installed on the fiber score 101C with a field sequential type TV camera
A signal cable 1070.
107D is extended, and this signal cable 107
Signal connectors 108G and 108 are installed at the ends of G and 107D.
D is provided.

Light source connectors 106A, 106B, 106C.

106D and 106E are connected to the light source device 103, signal connectors 108A and 108C are connected to the frame sequential video processor 102A, and signal connectors 1088.108
0 is connected to color mosaic video processor 102B.

As described in the fourth embodiment, the frame sequential video processor 102A and the color mosaic video processor 102B are each provided with a current consumption detection circuit 27, and the electronic endoscopes 101A and 101B connected thereto are provided with the current consumption detection circuit 27. The determination is made by detecting the current consumption of the external TV cameras 109C and 109D, and the drive clock is corrected and gain adjusted appropriately.

Other configurations, operations, and effects are the same as in the fourth and fifth practical examples.

[Effects of the Invention] As explained above, according to the present invention, the type of endoscope can be automatically detected without increasing the number of electrical contacts of the connector, which improves the operability of the scope connector. In addition, it is possible to obtain high-quality endoscopic images by setting optimal driving conditions or signal processing conditions for the connected endoscope.

[Brief explanation of drawings]

1 and 2 relate to the first embodiment of the present invention, FIG. 1 is a block diagram explaining the overall configuration of the electronic endoscope device, and FIG. 2 is a block diagram of the drive waveform correction circuit and the current consumption detection circuit. circuit diagram,
Figures 3 to 5 relate to the second embodiment of the present invention;
The figure is a block diagram of the second embodiment without showing the main parts, FIG. 4 is a circuit diagram of the control limiting circuit, FIG. 5 is a control characteristic diagram of the gain control amplifier, and FIG. 6 is a block diagram of the third embodiment of the present invention. Accordingly, FIG. 7, an explanatory diagram of the consumption current detection means, relates to the fourth embodiment of the present invention,
A schematic circuit diagram of an endoscope, FIG. 8, is a block diagram illustrating the overall configuration of an electronic endoscope device, and FIG. 9 is a block diagram illustrating a sixth embodiment of the present invention. FIG. 10, an explanatory diagram of the electronic endoscope device, relates to the seventh embodiment of the present invention, and FIGS. 11 and 12, an explanatory diagram of the entire endoscope device, relate to the prior art, and FIG. is the overall configuration diagram of the electronic endoscope, Part 1
FIG. 2 is a block diagram of the electronic endoscope. 1... Electronic endoscope device 2... Endoscope 3... Light source device 4... Control device 23... Solid-state image sensor 24... Video signal processing device 26... Drive waveform correction Circuit 27...Current consumption detection circuit 28...Signal line 37...Driving power supply circuit 1st hook Fig. 2 Fig. 3 Fig. 8 Fig. 9

Claims (1)

[Scope of Claims] An imaging device having a solid-state imaging device that converts a subject image into an electrical signal; a driving device that outputs a drive signal to the imaging device to drive the solid-state imaging device and output an image signal; A signal processing means that processes the image signal output from the image pickup means to visualize it; a display means that receives the image signal from the signal processing means and displays a subject image; and a current consumption of the image pickup means. Current consumption detection means detects the type of the imaging means and changes the setting of at least one of the driving condition of the driving means and the signal processing condition of the signal processing means. Electronic endoscope device.