JP2003290133A - Optical imaging device - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide an optical imaging device which has a common optical system so that it can be disposed in an endoscope insertion part, capable of obtaining not only ordinary macro images but also enlarged observation images with high resolution by low-coherent light, or the like. <P>SOLUTION: An objective optical system 13, a relay optical system 15 and so on are inserted into an insertion part 5 in this optical imaging device. A half mirror 16 disposed in a control part 6 forms the separation between an optical system on the side of an image pickup device 20 and a low-coherence optical system. Since a small aperture 18a and a large aperture 18b are respectively and separately disposed on these separated optical systems, pupil imaging optical systems 17a and 17b can respectively form a small-aperture image 43a or a large-aperture image 43b at a pupil position of the objective optical system 13. As a result, in the case of ordinary observation, the objective optical system 13 can make an observation over a wide range by means of a small number of apertures, while in the case of enlargement observation with low-coherent light, it can make an enlargement observation with high resolution by means of the large number of apertures. <P>COPYRIGHT: (C)2004,JPO

Description

Detailed Description of the Invention

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to an optical imaging apparatus for obtaining a high-resolution magnified image together with an ordinary macro image by an endoscope or the like.

[0002]

2. Description of the Related Art In recent years, endoscopes have been widely used in the medical field and the industrial field. Further, in addition to a normal observation image obtained by an endoscope, in order to make a detailed diagnosis of whether or not there is a lesion, for example, in Japanese Patent Laid-Open No. 6-154228, an optical tomographic image can be obtained using low interference light. There is something I did.

In this conventional example, since the objective optical system is commonly used for normal observation and for optical tomographic images using low interference light, the insertion portion of the endoscope can be made thin. it can.

[0004]

However, in the above-mentioned conventional example, the numerical aperture (NA) of the objective optical system is the same for normal observation and for optical tomographic images using low interference light. Therefore, there are problems that need to be improved.

That is, in normal use, first, in a state of normal observation, a wide area is macroscopically observed, and if there is a suspicious portion due to such observation, a part of it is observed. A method of examining the properties in detail by observing the image with an optical tomographic image is adopted.

In this case, in the conventional example, the objective optical system is commonly used, and its NA remains the same. Therefore, in a state suitable for normal observation, the resolution becomes insufficient in the state of the optical tomographic image, and conversely, when the state of the optical tomographic image is set to the state in which the high NA is high, In the case of observation, a wide field of view cannot be secured and only a narrow area can be observed.

In addition to the above, there is a conventional example in which separate optical systems are used for macro observation and for optical tomographic images, but in the case of an endoscope inserted into a body cavity or the like as described above. Is
It becomes difficult to reduce the diameter.

If different optical systems are adopted,
When the device becomes larger and the suspicious portion in the image for macro observation is to be magnified and observed by an optical tomographic image, the position in the macro image to be magnified and observed by the optical tomographic image is the distance or the like. There is a drawback that it tends to change with changes.

(Purpose of the Invention) The present invention has been made in view of the above-mentioned points. A part of an optical system is made common so that it can be arranged also in an endoscope insertion portion, etc. ,
It is an object of the present invention to provide a convenient optical imaging device capable of obtaining a magnified observation image with high resolution due to low coherence light or the like.

Further, it can be arranged in the endoscope insertion portion with a reduced diameter, and a normal macro image and a magnified observation image with high resolution due to low coherent light can be obtained in a convenient state. It is also an object to provide an endoscope for optical imaging.

[0011]

[Means for Solving the Problems] Illumination means, an optical system for forming an image of an illuminated object, an image pickup means for picking up the formed image, a low interference light source, and a light source for introducing the low interference light to the object. Further, there is an optical system that guides the light reflected from the subject to the low interferometer, and a signal processing unit that constructs an image from the interference signal obtained from the low interferometer. At least part of the system is the same, and the numerical aperture of the optical system focused on the image sensor is smaller than the numerical aperture of the optical system when light is guided to the low interferometer. It is possible to arrange an optical system that can be placed in the same place, and by setting such a numerical aperture, it is possible to obtain a normal macro image and a magnified observation image with high resolution due to low coherence light etc. Able to provide an optical imaging device with good performance

[0012]

BEST MODE FOR CARRYING OUT THE INVENTION Embodiments of the present invention will be described below with reference to the drawings. (First Embodiment) FIGS. 1 to 5 relate to a first embodiment of the present invention, and FIG. 1 shows an overall configuration of an endoscope apparatus of a first embodiment of an optical imaging apparatus of the present invention. 2 shows the internal configuration of the control device, FIG. 3 shows the configuration of the gimbal mirror, FIG. 4 shows a display example on the monitor, and FIG. 5 shows the internal configuration of the control device of the modified example.

As shown in FIG. 1, an endoscope apparatus 1 as a first embodiment for realizing the optical imaging apparatus of the present invention.
Is an endoscope 2 that can be inserted into a body cavity, a control device 3 that is connected to the endoscope 2 and that supplies illumination light and the like to the endoscope 2 and that performs image processing and control operations. The monitor 4 is connected to the control device 3 and displays an endoscopic image and a high-definition magnified image.

The endoscope 2 has a hard insertion portion 5 to be inserted into a body cavity, and an operation portion 6 which is formed at the rear end of the insertion portion 5 with a large width and which is grasped by an operator. . The outer cover of the insertion portion 5 is formed of a hard cylindrical tube, and an optical system having a function of transmitting light to the rear side, a light guide member for transmitting illumination light, an image formation, and the like, as described below, inside the cylindrical tube. Are arranged.

The endoscope 2 has illumination light (specifically, white light) in the insertion portion 5 and the operation portion 6 for normal observation.
A fiber bundle 7 as a light guide for transmitting the light is inserted, the fiber bundle 7 is extended to the outside from the operation unit 6, and its end is connected to the control device 3.

As shown in FIG. 2, the light source device 8 provided inside the control device 3 has a lamp 9 for generating white light and a condenser lens 10 for condensing this light on the end face of the fiber bundle 7. The light incident on the end face of the fiber bundle 7 is transmitted by the fiber bundle 7, and further spreads forward from the end face fixed to the end portion in the insertion portion 5 through the illumination optical system 11 and is emitted. The subject 12 side is illuminated.

It should be noted that the fiber bundle 7 is branched into two in the operation section 6 and is inserted into the insertion section 5 into two, so that the two illumination optical systems 11 are opposed to the two end faces. It is arranged. In addition, as described in other embodiments to be described later, the fiber bundle 7 has the insertion portion 5
It may be inserted in a circular shape inside.

An objective optical system 13 is arranged at the center between the two illumination optical systems 11 at the tip of the insertion section 5, and the light forming an image by the objective optical system 13 is arranged in the insertion section 5. It is transmitted (guided) by the relay optical system 15 so as to be relayed to the rear side. Although only one relay optical system 15 is shown in FIG. 1, the number may be increased depending on the length of the insertion portion 5.

The light transmitted by the relay optical system 15 so as to relay the image to the rear side is branched by the half mirror 16 in the operation unit 6. The light reflected by the half mirror 16 forms an image on the image pickup device 20 via the first pupil image-forming optical system 17a and the first diaphragm 18a, and further via the camera image-forming optical system 19.

The image formed on the image pickup device 20 is photoelectrically converted, and passes through a signal line 21 to a camera control unit (hereinafter abbreviated as CCU) inside the control device 3 shown in FIG.
The image signal component captured by the image sensor 20 is extracted by the CCU 22 by the correlated double sampling and is subjected to color separation to generate a standard video signal. Sent to.

The image signal sent to the arithmetic circuit 23 (picked up by the image pickup device 20) is combined with an enlarged image described later and output to the monitor 4, and on the display surface of the monitor 4, for example, FIG.
As shown in (A), the image 4a of the image sensor 20 is displayed as an endoscopic image.

Further, in the present embodiment, a light source & detection unit 24 is provided inside the control device 3 for generating light of low coherence and detecting return light from the subject 12 side. .

The light source & detection section 24 is, for example, an ultra-high brightness light emitting diode (hereinafter, referred to as SLD) which generates light with low coherence.
The light having low coherence from the SLD 25 is condensed by the condenser lens 26 and is incident on one end face of the optical fiber 27a. The optical fiber 27 a is extended from the control device 3 to the outside, and the other end is fixed inside the operation portion 6 of the endoscope 2.

The optical fiber 27a is connected to the other optical fiber 2 by the fiber coupler 28 in the middle of the control device 3.
Optically coupled to 7b. Therefore, the low-coherence light from the SLD 25 incident on the optical fiber 27a is transmitted to the other end face on the operation unit 6 side, and is optically coupled by the fiber coupler unit 28 to form a reference side optical path. 27
The light is also branched to the b side, and this light is modulated by a fiber modulator 29 formed by a piezo element or the like on the way.

The fiber modulator 29 is driven by the arithmetic circuit 23 to modulate the light guided by the optical fiber 27b. The optical path length side from the fiber coupler section 28 to the operation section 6 side by the optical fiber 27a or the like is the measurement side optical path length.

The light transmitted through the optical fiber 27b via the fiber modulator 29 is arranged opposite to one end face of the optical fiber 27b, and the stage 32 is provided by a collimator lens 31 forming a reference light side optical path length adjusting mechanism 30. The parallel beam is incident on the mirror 33 arranged at, and is reflected by the mirror 33.

The light reflected by the mirror 33 passes through the fiber modulator 29 and is mixed by the fiber coupler 28 with the return light on the optical fiber 27a side. in this case,
The difference in optical path length between the reference light side optical path length and the measurement side optical path length is SLD.
If it is within the coherence length of the light with low coherence by 25, it becomes interference light, and if it is longer than the coherence length of the light with low coherence, it does not interfere.

The light mixed by the fiber coupler 28 is collected from the other end face of the optical fiber 27b to the condenser lens 34.
Is collected by the photodetector (abbreviated as PD in FIG. 2) 3
Light is received at 5.

As described above, since the optical fiber 27b is optically coupled with the other optical fiber 27a by the fiber coupler 28 in the middle, the reflected light at the reference light side optical path length adjusting mechanism 30 is the other optical fiber 27a. The return light received at the end face of the optical fiber is mixed with the fiber coupler unit 28. That is, from the fiber coupler unit 28 to the reference light side optical path length adjusting mechanism 30.
The optical path length reaching the side is the reference optical path length. And
If the reference-side optical path length and the measurement-side optical path length are within the coherence length of the low-coherence light, the photodetector 35 detects the light as interference light. Therefore, the light source & detector 24
The detecting section in has a function as an interferometer.

The signal photoelectrically converted by the photodetector 35 is input to the arithmetic circuit 23, which demodulates the signal detected by the photodetector 35 and extracts the interference light component.

Further, the arithmetic circuit 23 sends a control signal to the stage 32 by an instruction operation from the front panel portion of the control device 3 or a keyboard 36 connected to the control device 3, and the stage 32 is indicated by an arrow A. The reference side optical path length can be changed by moving the mirror 33 to the position of the mirror 33.

A scanner driving device 37 is provided inside the control device 3, and the scanner driving device 37 drives the gimbal scanner 39 shown in FIG. 1 via a signal line 38. The scanner driving device 37 is connected to the arithmetic circuit 23.

Then, the arithmetic circuit 23 demodulates and extracts the signal of the interference light component from the signal from the photodetector 35, and A / D-converts the signal and stores it in the internal memory. Two-dimensional image data of a tomographic image by light with low coherence is generated by storing the data in association with the scanning.

As shown in FIG. 1, a collimator optical system 41 is arranged so as to face the end face of the optical fiber 27a fixed inside the operating portion 6, and the collimator optical system 41 emits light from the end face of the optical fiber 27a. The light is collimated and driven by the scanner driving device 37.
It is incident on a gimbal scanner 39 as a dimensional scanner. The mirror surface of the gimbal scanner 39 is set at an angle of 45 ° with the optical axis of the collimator optical system 41.

A schematic structure of the gimbal scanner 39 is shown in FIG. The gimbal scanner 39 holds the central mirror surface 39a by a first hinge portion 39b so as to be tiltable in the horizontal direction, for example, and at the same time, the first hinge portion 39b is held.
A second hinge portion 39c, which is orthogonal to the holding direction of the first hinge portion 39b, is held on the outer side of b so as to be tiltable in the vertical direction, and magnetically or electrostatically by a scanner driving signal from the scanner driving device. Mirror surface 39 by drive mechanism
2a is tilted two-dimensionally, and the light incident by the collimator optical system 41 is two-dimensionally scanned.

As shown in FIG. 1, this gimbal scanner 3
The light reflected by 9 is converted by the pupil diameter conversion optical system 42 composed of a pair of convex lenses into a parallel beam in which the diameter of the light beam is increased. The pupil diameter conversion optical system 42 expands the diameter of the light beam to provide the gimbal scanner 3
As for 9, a small size can be adopted.

The parallel beam passes through the second diaphragm 18b and is condensed by the second pupil image-forming optical system 17b. A part of the parallel beam is transmitted by the half mirror 16 and the relay optical system 1
5, the light is incident on the objective optical system 13 via the relay optical system 15, and is condensed by the objective optical system 13 to be condensed and irradiated to the subject 12 side.

Then, the reflected light from the subject 12 is guided to the end face of the optical fiber 27a via the reverse path. The subject 12 transmitted by this optical fiber 27a
A part of the return light from the side is branched to the optical fiber 27b side by the fiber coupler section 28 and is received by the photodetector 35.

In the present embodiment, as shown in FIG. 1, in addition to the illuminating means (specifically, the fiber bundle 7 and the illuminating optical system 11) for illuminating the inside of the insertion portion 5, the illuminating means illuminates. An objective optical system 13 for forming an image of the subject 12 thus formed and a relay optical system 15 for transmitting the optical image to the rear side of the operation unit 6 are arranged.

The objective optical system 13 and the relay optical system 15
Has a configuration similar to that of a normal optical endoscope,
Inside the operation unit 6, there is provided a branching unit that splits light into a reflected light side and a transmitted light side by the half mirror 16.
By this branching means, the reflected light side is guided to an image pickup means for performing imaging for normal observation, and the transmitted light side guides low interference light to the subject 12 side and returns from the subject 12 side. A low interference light side optical system that guides light to (on the side of the detector 35 that functions as an interferometer) is arranged. Then, the branching means can obtain the image information for normal observation and the enlarged image information by (scanning) the low interference light.

As described above, in this embodiment, the objective optical system 13 and the relay optical system 15 arranged in the insertion portion 5 are commonly used for normal observation (macro observation) and magnified observation (micro observation) with low interference light. By doing so, the diameter of the insertion portion 5 can be reduced.

Further, in the present embodiment, the first pupil imaging optical system 17a, the first diaphragm 18a having a small diaphragm diameter, and the second diaphragm 18a are provided on the respective optical paths branched by the half mirror 16 inside the operation section 6. Pupil imaging optical system 17b and a second diaphragm 18b having a large diaphragm diameter are arranged respectively, and the first diaphragm 1
The image 43a of 8a and the image 43b of the second diaphragm 18b are connected to the pupil position of the objective optical system 13.

That is, in FIG. 1, the image (aperture image) 43a of the first aperture 18a becomes a small aperture image on the optical axis O as shown by the dotted line, whereas the image of the second aperture 18b.
The image (aperture image) 43b is a large size aperture image on the optical axis O as shown by the solid line.

Then, in the image pickup device 20 for normal observation,
The numerical aperture (hereinafter abbreviated as NA) of the objective optical system 13 is made substantially small so that only the light that has passed through the aperture of the image 43a of the first diaphragm 18a functions for image formation. The second diaphragm 18b for light with low coherence.
It functions as the NA of the high-resolution objective optical system 13 so that the light passing through the large opening portion of the image 43b of FIG.

In the present embodiment, when low coherence light is used, the NA is increased to obtain a high resolution, and a small area in the center of the normal observation range can be magnified and observed. .

In FIG. 1, a long dotted line shows an off-axis chief ray when low coherence light is used. In this case, the observation range of the object 12 is an optical axis O indicated by a chain line (long dotted line). (Indicated by) and the small range indicated by the chief ray. Since the gimbal scanner 39 is also scanned in the direction perpendicular to the paper surface of FIG. 1, it is possible to observe with a small size in the direction perpendicular to the paper surface.

Further, by generating image data from a large number of intensity data of interference light components in response to scanning by the gimbal scanner 39, it is possible to construct a high resolution and high definition image.

On the other hand, for normal observation, the NA of the objective optical system 13 is substantially reduced so that a wide area is not darkened (due to the light beam) on the peripheral side of the visual field. The image pickup device 20 can form an image so that a good image that is easy to observe can be obtained.

Then, as shown in FIG. 4A, the normal image (macro image) 4a by the image pickup device 20 and the (high-definition) enlarged image 4b by the low coherence light are displayed so as to be adjacent to each other. The observation range 4c of the magnified image 4b when low coherence light is used is displayed at the center of the normal image so that the observation range 4c of the magnified image 4b can be easily seen from the normal image 4a.

The gimbal scanner 39 is driven one-dimensionally in the horizontal direction, for example, and in that case, the stage 32 of the reference-light-side optical path length adjusting mechanism 30 is synchronously scanned, so that the depth direction of the subject 12 is increased. A tomographic image when scanned is also obtained.

In this case, for example, as shown in FIG. 4B, a tomographic image 4d is displayed adjacent to the normal image 4a. In that case, on the normal image 4a side, for example, a line indicating a cross-sectional position in the tomographic image 4d. 4e is displayed. It should be noted that the gimbal scanner 39 is one-dimensionally driven not in the horizontal direction but in the vertical direction, and the stage 32 is scanned in synchronization with this, so that the depth of the subject 12 along the surface in the vertical direction is increased. It is also possible to obtain a tomographic image when scanning in the direction.

The operation of this embodiment having such a configuration will be described below. When the controller 3 is turned on,
The subject 12 side is illuminated by the illumination light from the light source device 8, and the illuminated subject 12 is imaged by the objective optical system 13 functioning as a small NA, and transmitted to the rear side by the relay optical system 15.

Then, the light is reflected by the half mirror 16, is imaged on the image pickup device 20 via the pupil image-forming optical system 17a, the diaphragm 18a, and the camera image-forming optical system 19, and is photoelectrically converted. The output signal is converted into a video signal by the CCU 22 by the image pickup device 20, is output to the monitor 4 via the arithmetic circuit 23, and is a macro image picked up by the image pickup device 20 as shown in FIG. 4A or 4B. Image 4a as
Is displayed.

On the other hand, the light of low coherence emitted from the SLD 25 is collected and incident on the optical fiber 27a, and this light is partly branched to the optical fiber 27b side by the fiber coupler 28, and the light is referred to. Reciprocates along the optical path on the light side.

The light guided to the tip side by the optical fiber 27a is emitted from the end face in the operation portion 6, collimated by the collimator optical system 41 and incident on the gimbal scanner 39. This gimbal scanner 39 is a scanner. Drive device 3
The lens 7 is two-dimensionally tilt-driven, and the reflected light is two-dimensionally scanned.

The light beam reflected by the gimbal scanner 39 has its beam diameter expanded through the pupil diameter conversion optical system 42, passes through the second diaphragm 18b, and has a large beam diameter.
The light is guided to the relay optical system 15 side through the half mirror 16. After passing through the relay optical system 15, the objective optical system 13 condenses and irradiates the object 12 side so that the objective optical system 13 has an opening having a substantially outer diameter.

The reflected light on the side of the subject 12 passes through the opposite optical path and is condensed and incident on the front end surface of the optical fiber 27a, and the light thereof has low coherence with the optical path length on the reference light side by the fiber coupler 28. Those that are within the coherence length of light are coherent light,
The light is received by the photodetector 35.

The signal photoelectrically converted by the photodetector 35 is input to the arithmetic circuit 23, which is two-dimensionally scanned and the interference light component modulated by the fiber modulator 29 is extracted. The signal is demodulated, converted into digital data by an internal A / D converter, and the signal input in time series is stored in the memory to generate two-dimensional image data.

The image data is read out as an analog video signal by the D / A converter, and is output to the monitor 4 together with the video signal input from the CCU 22 side. The display surface of the monitor 4 is shown in FIG. As shown in FIG.
Is displayed as a high-definition enlarged image 4b together with the normal image 4a.

When a scan change instruction is input from the keyboard 36, the scanner drive device 37 generates a one-dimensional drive signal, which is transmitted via the signal line 38 to drive the scanner 39 one-dimensionally. Further, the arithmetic circuit 23 is the stage 3
By reciprocating 2 in synchronization with the scanner 39, a tomographic image is constructed by a signal from the photodetector 35. In this case, as shown in FIG. 4B, a tomographic image 4d is displayed on the display surface of the monitor 4 together with the normal image 4a by the image sensor 20.

According to the present embodiment, the subject 12 in a wide range can be observed as a normal image like an ordinary endoscope, and the narrow area at the center can be enhanced by the magnified image by the low coherence light. It can also be observed at resolution.

Next, a typical case of NA in this embodiment will be described. The following formula (1) shows the relationship of the resolution of the objective optical system 13. r = 0.56λ / NA (1) Here, r represents a resolvable length, and λ represents the wavelength of light used.

For example, in the case of a macro image, when considering an image pickup by the image pickup device 20 in which 500 × 500 pixels are arranged in a square of 2 mm square, one pixel becomes a pixel of 4 μm square. In this case, it suffices that the half length 2 μm can be decomposed by the sampling theorem, and the wavelength λ is 0.5 μm near the center of white light.

In this case, the equation (1) is 2 = 0.56 × 0.5 / NA And NA = 0.14.

On the other hand, assuming that at least about 1 μm is required as the resolvable length r for the micro image, the equation (1) is 1 = 0.56 × 0.8 / NA. Here, as the wavelength λ, a wavelength of about 0.
8 μm. In this case, NA = 0.448 or more.

Therefore, the NA in the case of the micro image is 0.448 / 0.14≅3 in the case of the macro image. That is, the NA in the case of a micro image is three times or more that of the macro image.

According to the present embodiment, since the enlarged micro image by the low coherence light is displayed in the narrow area at the center of the macro image, the normal endoscopic diagnosis can be performed by the macro image. In addition to being able to carry out the operation, it is possible to display a micro image having a high NA and high resolution in an enlarged manner in the central portion thereof, so that it is possible to provide an environment in which more detailed diagnosis can be easily performed at the cell level.

In this case, since the common objective optical system 13 is used to observe a macro image and a micro image in a state where the NA is substantially different, the micro image in the macro image is The position to be observed remains unchanged within a predetermined range of the central portion, and the alignment when observing with a micro image becomes easy.

Further, in the present embodiment, the objective optical system 13 and the relay optical system 15 are inserted and arranged in the insertion section 5 as in the case of a normal endoscope, and the optical system is also used in the case of low coherence light. Since the configuration is commonly used, the diameter of the insertion portion 5 can be reduced. Therefore, the insertion portion 5 of the present embodiment can be inserted through the small insertion hole, and the pain given to the patient can be reduced.

In the above description, the case of using the low coherence light has been described, but this embodiment can be similarly applied to the case of using the confocal optical system.

FIG. 5 shows the configuration of the control device 3B when a confocal optical system is used. In this case, the endoscope 2 has the same configuration as that of FIG.

In this case, instead of the light source & detection unit 24 of FIG. 2, a light source & detection unit 24B having a simple structure is adopted. The light of, for example, a laser diode 45 as a light source is condensed by a condenser lens 46 and is incident on one end of the optical fiber 27a, the light is transmitted by the optical fiber 27a, and the other end surface inside the operation unit 6 shown in FIG. It is emitted from the (front end surface). In this case, the size of the front end surface of the optical fiber 27a is sufficiently small, and the same function as a pinhole can be achieved. Then, similarly to the above, through the gimbal scanner 39 and the like, the objective optical system 13 converges and irradiates the object 12 side with a high NA.

Then, only the light reflected from the focus position (focal point) of the objective optical system 13 follows the reverse optical path of the reflected light on the side of the subject 12 and enters the front end surface of the optical fiber 27a.
There is a component of reflected light from a portion other than the focal point of the objective optical system 13 that returns through the objective optical system 13 and the like, and these reach the periphery of the optical fiber 27a, but do not enter the small end face of the optical fiber 27a.

That is, the front end surface of the optical fiber 27a and the focal point of the objective optical system 13 are in a conjugate relationship via the optical system between them. Then, the light from other than the part having the conjugate relationship is excluded.

The return light incident on the optical fiber 27a receives the fiber circulator section 47 provided in the light source & detection section 24B.
Is guided to the other optical fiber 27c, and is received by the photodetector 49 through the condenser lens 48.

The signal photoelectrically converted by the photodetector 49 is input to the arithmetic circuit 23. This arithmetic circuit 23 performs almost the same processing as that for which the demodulation processing in the arithmetic circuit 23 of FIG. 2 is omitted. The image captured by the image sensor 20 by the CCU 22 is combined, and the monitor 4 displays a normal image 4a and a high-definition enlarged image 4b as shown in FIG.
This modification also has substantially the same effect as that of the first embodiment.

(Second Embodiment) Next, a second embodiment of the present invention will be described with reference to FIG. FIG. 6 shows an endoscope apparatus 1C according to the second embodiment of the present invention. The endoscope device 1C includes an endoscope 2C and a control device 3 (or 3
B) and a monitor 4.

The endoscope 2C shown in FIG. 6 is the same as the endoscope 2 shown in FIG. 1 except that the insertion portion 5 has the same structure and the optical system inside the operation portion 6 is partially different. Specifically, in the first embodiment, the light that has passed through the relay optical system 15 is branched by the half mirror 16 and then the pupil imaging optical systems 17a, 17b and 2 arranged on the two branched optical paths. Although the two diaphragms 18a and 18b are arranged, in the present embodiment, the pupil imaging optical system 17 and the variable diaphragm 51 are arranged on the common optical path on the front side (the relay optical system 15 side) that branches. .

The variable diaphragm 51 is connected by a signal line 52 to, for example, the arithmetic circuit 23 inside the control device 3 or 3B, and the diaphragm diameter can be varied via the arithmetic circuit 23. For example, normally, a small aperture diameter 51a is set, and in this state, a normal image captured by the image sensor 20 is displayed on the monitor 4, and when a switching instruction operation is performed from the keyboard 36 shown in FIG. The diameter 51b is set. At the same time as the switching, the arithmetic circuit 23 receives a signal obtained by receiving the image displayed on the monitor 4 by the photodetector 35 or 49,
That is, an enlarged image (or tomographic image) with low coherence light or an enlarged image with a confocal optical system is displayed.

The other structure is the same as that of the first embodiment. In the present embodiment, the variable diaphragm 51 is usually set to a small diaphragm diameter 51a state, and observation similar to that of a normal endoscope can be performed. Then, for a portion that is desired to be enlarged and observed, the arithmetic circuit 2 is set by setting the portion in the central portion of the observation visual field and performing a switching instruction operation.
3 sets the variable diaphragm 51 to a large diaphragm diameter 51b state,
An enlarged image (or a tomographic image) by low coherence light or an enlarged image by a confocal optical system is displayed.

In the present embodiment, since the common optical system portion in the first embodiment is used more, the entire optical system can be made smaller. Others have almost the same effect.

The size of the diaphragm diameter of the variable diaphragm 51 may be changed according to the resolution and the observation range.
Specifically, when performing magnified image (or tomographic image) with low coherence light or magnified observation with a confocal optical system, the maximum resolution is determined by the maximum NA, but it is less than the observation range in that case. When a wide range is to be observed, an instruction operation is performed from a keyboard or the like to reduce the NA of the variable diaphragm 51 via the signal line 52 and to scan a wide two-dimensional scanning range of the gimbal scanner 39. Then, a wide range can be set as the observation range, and in this case, the NA may be made small so that the peripheral side can be observed with the same brightness as the central side.

(Third Embodiment) Next, a third embodiment of the present invention will be described with reference to FIGS. FIG. 7 shows an endoscope apparatus 1D according to the third embodiment of the present invention. The endoscope device 1D includes an endoscope 2D, a control device 3 (or 3B), and a monitor 4. An endoscope 2D shown in FIG. 7 is the same as the endoscope 2 shown in FIG.
Is equipped with a double focus lens 54.

Further, in this embodiment, the optical fiber 27a is used.
The two-dimensional scanner including the piezo element 55 holds the front end surface of the optical element, that is, the position where the light is emitted and the image forming surface. The piezo element 55 is driven by the scanner driving device 37.
Drive through 6 and drive as shown by the solid and thick long dashed lines in FIG. It should be noted that it is also possible to drive in the direction perpendicular to the paper surface.

In the case of FIG. 7, the light from the front end surface of the optical fiber 27a passes through the image forming optical system 57, the second diaphragm 18b and the second pupil image forming optical system 17b, and is relayed on the front side of the half mirror 16. The light is guided to the optical system 15 side. FIG. 8 shows a configuration example of the double focus lens 54. For example, the front lens side in the objective optical system 13 shown in FIG. 7 is composed of a convex lens 57 and a diffractive lens 58 arranged in front of it.

The diffractive lens 58 has concavo-convex concavo-convex portions, and the 0th-order light is used for the normal observation light to focus the position P.
The objective optical system 13 is made to function as a long focal length by focusing at a, while the low coherence light or the light of the confocal optical system is used at the focus position Pb by using the first-order diffracted light. In this case, the objective optical system 13 is made to function as a short focal length.

As a typical example, the focal length when focusing on the focal position Pa is 3 of the focal length when focusing on the focal position Pb using the first-order diffracted light.
Double or more (from the same request for resolution as in the case described in the first embodiment). Other configurations are similar to those of the first embodiment.

According to the present embodiment, in the case of normal observation, it is made to function as the objective optical system 13 having a long focal length and a small NA, while in the case of observing with low coherence light or confocal optical system. The objective optical system 13 having a short focal length and a large NA and a high resolution is caused to function.

In the present embodiment, the distance for observing the subject 12 is different between normal observation and low coherence light or confocal optical system. However, in the case of the present embodiment, in the case of normal observation, the focal length is long and non-telecentric, so that a wider range of observation is easier than in the first embodiment. When it is desired to magnify and observe a part of it in more detail, it is possible to magnify and display a micro image with low coherence light or a confocal optical system, and it is possible to provide an environment in which it is easy to make a detailed diagnosis at the cell level.

Further, in the present embodiment as well, the inside of the insertion portion 5 is configured to be commonly used for normal observation and for low coherence light or confocal optical system.
Can be reduced in diameter.

(Fourth Embodiment) Next, a fourth embodiment of the present invention will be described with reference to FIG. FIG. 9 shows an endoscope apparatus 1E according to the fourth embodiment of the present invention. The endoscope device 1E includes an endoscope 2E, a control device 3E, and a monitor 4. The endoscope 2E shown in FIG. 9 is the same as the endoscope 2 shown in FIG.
The focal length can be changed by changing the refractive index by turning ON / OFF the voltage application via the line 2.

Further, in the present embodiment, the control device 3E has a structure in which the light source & detection unit 24E having a function corresponding to the light source & detection unit 24B in the control device 3B of FIG. The optical fiber 27a is not used.

That is, after the light of the laser diode 45 is made into a parallel beam by the collimator lens 64, a part of the light is transmitted by the half mirror 65, is condensed by the condenser lens 66, and is arranged at the focus position. The light enters the collimator optical system 41 through the pinhole of the pinhole forming element 67.

The collimated beam from the collimator optical system 41 is made to have a predetermined beam diameter by the second diaphragm 18b, reflected by the gimbal scanner 39, incident on the second pupil imaging optical system 17b, and further a half mirror. The light is guided to the relay optical system 15 side via 16.

After being guided by the relay optical system 15, the liquid crystal lens 61 of the objective optical system 13 focuses and irradiates the subject 12 side in a short focus. Then, the reflected light on the side of the subject 12 enters the pinhole forming element 67 through the reverse path. In this case, only the reflected light at the focal position of the objective optical system 13 enters the condenser lens 66 through the pinhole, is further reflected by the half mirror 65 and is partially condensed by the condenser lens 68. The light is received by the photodetector 49.

The signal of the photodetector 49 is amplified by the amplifier 69 and then input to the arithmetic circuit 23 inside the control device 3E through the signal line 70. The other configurations are the same as those of (the modification of) the first embodiment.

In this embodiment, in the case of normal observation, the focal length of the objective optical system 13 is lengthened by reducing the refractive index of the liquid crystal lens 61, and the confocal optical system is used. In order to increase the refractive index of the liquid crystal lens 61, the focal length of the objective optical system 13 is shortened. Also,
For normal observation, the diaphragm 18a has a small NA, while when using a confocal optical system, the diaphragm 18b has a large NA for high resolution.

In this embodiment, the normal observation and the micro observation by the confocal optical system can be used in a time-division manner instead of the simultaneous observation. The effect in this case is almost the same as that of the third embodiment.

In this embodiment, the light source & detection unit 24E is provided inside the operation unit 6 by the confocal optical system. However, the light source & detection unit 24 shown in FIG. It may be provided so that it can be applied even when low coherence light is used.

(Fifth Embodiment) Next, a fifth embodiment of the present invention will be described with reference to FIG. FIG. 10 shows an endoscope apparatus 1F according to the fifth embodiment of the present invention.
The endoscope device 1F includes an endoscope 2F and a control device 3 (or 3
B) and a monitor 4.

The endoscope 2F shown in FIG. 10 is the endoscope 2 shown in FIG.
In the above, as the objective optical system 13, for example, the front lens group of the objective optical system 13 can be moved in the optical axis O direction by an actuator 72 arranged in the vicinity thereof as a zoom optical system 71.

That is, the actuator 72 uses the signal line 73
According to the operation circuit 23 in the control device 3 (or 3B).
The zoom optical system 71 can be set to a state of normal observation and a state of observation with low coherence light or a confocal optical system by performing a switching instruction operation from a keyboard or the like.

Specifically, this zoom optical system 71 is composed of a lens group having a positive power of a convex lens and a negative power of a concave lens, and is set to the position shown by the dotted line in FIG. 10 for normal observation. Therefore, the focal length of the objective optical system 13 becomes long.

On the other hand, when the observation instruction by the low coherence light or the confocal optical system is given, the zoom optical system 71 is variably set from the position shown by the dotted line to the position shown by the solid line. The focal length of the objective optical system 13 becomes short.

In this case, as shown in FIG. 10, the focus is set to the same distance from the distal end surface of the insertion section 5.

The configuration of the operation section 6 in the endoscope 2F of the present embodiment is such that the pupil diameter conversion optical system 42 is omitted in the optical system in the operation section 6 of the endoscope 2 of FIG. The configuration is almost the same.

Specifically, the light emitted from the tip end surface of the optical fiber 27a is made into a parallel beam by the collimator optical system 41, made into a predetermined beam diameter by the second diaphragm 18b, and made incident on the gimbal scanner 39. , The reflected light thereof is generated without using the pupil diameter conversion optical system 42.
It is incident on b. According to the present embodiment, although time division is performed, it is easy to widen the observation range of normal observation (macro image) as compared with the first embodiment, as in the fourth and fifth embodiments. There is an effect that the observation distances of the macro image and the micro image can be equalized.

(Sixth Embodiment) Next, a sixth embodiment of the present invention will be described with reference to FIG. FIG. 11 shows an endoscope apparatus 1G according to the sixth embodiment of the present invention.
The endoscope device 1G includes an endoscope 2G and a control device 3 (or 3
B) and a monitor 4.

The endoscope 2G shown in FIG. 11 is the endoscope 2 of FIG.
In the above, the insertion section 5 and the operation section 6 are detachable. Therefore, the rear end of the insertion portion 5 and the front end portion of the operation portion 6 can be detachably connected by the attachment portion (connection portion) 75.

In this case, since the fiber bundle 7 is divided into two parts (on the insertion part 5 side and the operation part 6 side) at the attachment part 75, in this embodiment, the front end of the fiber bundle 7a on the operation part 6 side is divided. A diffusing plate 76 is provided in this portion,
The illumination light is transmitted to the fiber bundle 7b on the insertion portion 5 side via the cable 6. Then, inside the insertion part 5, 2
It branches into books.

A second relay optical system 77 is arranged on the optical path between the relay optical system 15 in the insertion section 5 and the half mirror 16 in the operation section 6. In this second relay optical system 77, one convex lens 77a is arranged on the insertion portion side and the other convex lens 77b is arranged on the operation portion 6 side, and a pair of lenses 77a, 77b are used to form parallel beams at the mounting portion 75. It is designed to guide light.

In the present embodiment, the optical fiber 27a
The tip of the piezo element 55 is, for example, as shown in FIG.
The light emitted from the tip of the optical fiber 27a is two-dimensionally driven by the imaging optical system 57 to form a parallel beam,
After being made to have a predetermined beam diameter by the diaphragm 18b, the light is condensed by the second pupil imaging optical system 17b, passes through the half mirror 16 and one lens 77b of the second relay optical system 77, and then the insertion portion 5 side. Is guided to the lens 77a. Others are first
The configuration is similar to that of the above embodiment.

In this embodiment, the insertion portion 5 is detachably attached to the operation portion 6, so that, for example, insertion portions 5 having different lengths can be attached and used.

Therefore, it is possible to use the endoscope 2G having a different insertion portion length depending on the part to be used. Further, the insertion section 5 having a different focal length of the objective optical system 13 may be attached to increase the resolution, and the resolution may be changed to an appropriate one according to the site to be used. .

Therefore, according to the present embodiment, in addition to the effects of the first embodiment, it can be used in a wider range of applications, and an observation image can be obtained in a state suitable for the application. You can also

Although the present embodiment has been described in the case of a structure similar to that of the first embodiment, for example, in the first embodiment, the insertion portion 5 and the operation portion 6 are detachable. Alternatively, it may be applied to other embodiments.

12 (A) and 12 (B) are views showing the insertion portion 5 and the operating portion 6 in the modification of the present embodiment as viewed from the mounting portion side, respectively.

In this modified example, FIG.
As shown in FIG. 5, the ring-shaped fiber bundle 7b is inserted inside the hard outer tube 81 of the insertion portion 5, and a lens tube (not shown) is inserted along the central axis of the ring (the relay optical system 15 and thereafter). A lens 77a (located near the edge) is attached.

On the other hand, an annular attachment portion 82 is provided so that the rear end of the insertion portion 5 of the operation portion 6 can be fitted and attached, for example, and faces the fiber bundle 7b (on the insertion portion 5 side) inside thereof. A white LED 83 is arranged in the annular portion, and a lens 77b is arranged inside the white LED 83 so as to face the lens 77a on the insertion portion 5 side.
This modified example has substantially the same effects as the sixth embodiment.

(Seventh Embodiment) Next, a seventh embodiment of the present invention will be described with reference to FIG. FIG. 13 shows an endoscope apparatus 1H according to the seventh embodiment of the present invention.
The endoscope device 1H includes an endoscope 2H and a control device 3 (or 3
B) and a monitor 4.

The endoscope 2H shown in FIG. 13 is, for example, as shown in FIG.
In the endoscope 2G described above, the fiber bundle 7b provided in the insertion portion 5 and the illumination optical system 11 at the tip thereof are removed, and the illumination light emitted from the tip surface of the fiber bundle 7a in the operation portion 6 is removed. The illumination optical system 85 collects the light, the second half mirror 86 partially reflects the light, and the illumination light is guided to the second relay optical system 77 side.

The emission angle of the illumination light emitted from the tip surface of the fiber bundle 7a is set to about the viewing angle when the image is formed on the image pickup device 20, so that the image pickup range can be illuminated efficiently. There is. Others are the same as those in FIG.

According to the present embodiment, the illumination light transmission means and the illumination optical system arranged in the insertion portion 5 can be eliminated, so that the insertion portion 5 can be made smaller in diameter. Others are first
The effect is almost the same as that of the embodiment.

(Eighth Embodiment) Next, an eighth embodiment of the present invention will be described with reference to FIG. FIG. 14 shows an endoscope apparatus 1I according to the eighth embodiment of the present invention.
The endoscope device 1I includes an endoscope 2I and a control device 3 (or 3
B) and a monitor 4.

The endoscope 2I shown in FIG. 14 is, for example, in the endoscope 2 of FIG. 1, in the vicinity of the tip of the optical fiber 27a,
The collimator optical system 41, the gimbal scanner 39, and the lens on the gimbal scanner 39 side (shown by 42 a) in the pupil diameter conversion optical system 42 are arranged on the XY stage 91.

This XY stage 91 is connected to the control device 3 (or 3B) (internal arithmetic circuit 23) via a signal line 92, and is operated in the X and Y directions orthogonal to the optical axis O by an instruction operation from a keyboard or the like. It is possible to move in two dimensions.

In the first to seventh embodiments, the observation range of the low coherence light or the confocal optical system is near the predetermined position of the central portion near the optical axis O in the observation range in the case of normal observation. However, in the present embodiment, it is possible to change the observation range by the low coherence light or the confocal optical system by making it possible to move one-dimensionally in the X or Y direction or two-dimensionally in the X and Y directions. I have to.

The amount of movement by the XY stage 91 is detected by a detection means such as an encoder (not shown), and the observation range by the low coherence light or the confocal optical system in that case is displayed to the user by a frame or the like in an image for normal observation. You may make it display so that it may be understood.

The other structure is similar to that of the first embodiment.

In the present embodiment, since the range for magnifying observation can be moved and changed, the user can change and set the range for magnifying observation so that it can be easily diagnosed, and the operability can be improved. Others have the same effects as those of the first embodiment.

The embodiments and the like configured by partially combining the above-described embodiments and the like also belong to the present invention.

For example, although the moving stage 91 is provided in the first embodiment in the eighth embodiment, it may be applied to other embodiments. Further, for example, in FIG. 11, the insertion section 5 and the operation section 6 are made detachable by the attachment section 75, but the configuration of the insertion section 5 and the operation section 6 in that case is not the configuration shown in FIG. The configuration of the embodiment may be adopted.

[Appendix] 5. Illuminating means, an optical system for forming an image of the illuminated object, an image pickup means for picking up the formed image, a low-interference light source, and a light that reflects the low-interference light to the object and reduces the light reflected from the object. There is an optical system leading to the interferometer and signal processing means for constructing an image from an interference signal obtained from a low interferometer, and at least a part of the optical system leading to the interferometer and the optical system leading to the interferometer are the same. An optical imaging apparatus characterized in that an object observation range of an optical system for forming an image on an image sensor is wider than an object observation range of the optical system when being guided to a low interferometer.

6. Illuminating means, an optical system for forming an image of the illuminated object, an imaging means for capturing the formed image, a coherent light source, a confocal optical system, and coherent light from the confocal optical system to the object. Further, there are an optical system for returning the reflected light from the subject to the confocal optical system and a signal processing means for constructing an image from the optical signal from the confocal optical system. At least a part of the optical system leading to the optical system is the same, and the object observation range of the optical system that forms an image on the image sensor is wider than the object observation range of the optical system when light is guided to the confocal optical system. Optical imaging device.

7. Illuminating means, an optical system for forming an image of the illuminated object, an image pickup means for picking up the formed image, a low-interference light source, and a light that reflects the low-interference light to the object and reduces the light reflected from the object. There is an optical system leading to the interferometer and signal processing means for constructing an image from an interference signal obtained from a low interferometer, and at least a part of the optical system leading to the interferometer and the optical system leading to the interferometer are the same. An optical imaging apparatus, wherein a diameter of an object observation range of an optical system when light is guided to a low interferometer is smaller than a diameter of an optical system of a common portion.

8. Illuminating means, an optical system for forming an image of the illuminated object, an imaging means for capturing the formed image, a coherent light source, a confocal optical system, and coherent light from the confocal optical system to the object. Further, there are an optical system for returning the reflected light from the subject to the confocal optical system and a signal processing means for constructing an image from the optical signal from the confocal optical system. At least a part of the optical system leading to the optical system is the same, and the diameter of the object observation range of the optical system when the light is guided to the confocal optical system is smaller than the optical system of the common part. Optical imaging device.

9. 3. The optical imaging apparatus according to claim 1, wherein the means for changing the numerical aperture has diaphragms having different apertures in the respective optical systems. 10. 3. The optical imaging apparatus according to claim 1, wherein the means for changing the numerical aperture changes the aperture diameter of the diaphragm. 11. 5. The optical imaging apparatus according to claim 3, wherein the means for changing the focal length is an optical system having two focal lengths.

12. 4. The means for changing the focal length is to change a part of the optics.
4. Optical imaging device of 4. 13. The numerical aperture of the optical system that forms an image of the subject on the image sensor is
The optical imaging apparatus according to claim 1, wherein the numerical aperture is ⅓ or less of the numerical aperture of the optical system that guides the light to the low interferometer. 14. The numerical aperture of the optical system that forms an image of the subject on the image sensor is
The optical imaging apparatus according to claim 2, wherein the numerical aperture is 1/3 or less of the numerical aperture of the optical system that guides the light to the confocal optical system.

15. The optical imaging apparatus according to claim 3, wherein a focal length of an optical system for forming an image of the subject on the image pickup device is three times or more of a focal length of an optical system for guiding light to the low interferometer. 16. The optical imaging apparatus according to claim 4, wherein a focal length of an optical system for forming an image of the subject on the image pickup device is three times or more of a focal length of an optical system for guiding light to the confocal optical system.

17. Illuminating means for illuminating the subject, an optical system for transmitting an image of the illuminated subject to the rear side in the insertion section, and an endoscope for forming an image on an image sensor provided in the operation section by the optical system, In an endoscope apparatus including a control device that is connected to the endoscope and performs an imaging process for displaying a normal image captured by an image sensor on a display unit, the operation unit includes an optical branching unit and the optical branching unit. A first optical system that forms an image of the optical system by the branching unit by the image pickup device, and low-coherence light is focused and irradiated to the subject side through the optical system, and the reflected light thereof is the control device. A second optical system for guiding light to the interferometer side provided in the optical system, and a second optical system for guiding the numerical aperture of the optical system to the interferometer side when forming an image of the imaging device. An endoscopic device characterized by being made smaller than a numerical aperture.

18. An illuminating means for illuminating the subject and an optical system for transmitting an image of the illuminated subject to the rear side in the insertion section, and an endoscope for forming an image on an image pickup device provided in the operation section by the optical system, A light branching unit on the operation unit, a first optical system for forming an image of the optical system by the light branching unit on the imaging device, and low-coherence light is focused on the subject side through the optical system. A second optical system for irradiating and guiding the reflected light to a means for detecting the interference light;
An endoscope characterized in that the numerical aperture of the optical system when forming an image of the image pickup element is smaller than the numerical aperture of the optical system when guiding light to the interferometer side.

19. An illuminating means for illuminating the subject and an optical system for transmitting an image of the illuminated subject to the rear side in the insertion section, and an endoscope for forming an image on an image pickup device provided in the operation section by the optical system, A light branching unit on the operation unit, a first optical system for forming an image of the optical system by the light branching unit on the image pickup device, and an optical system for converging and irradiating the object side, and condensing the light. A second optical system for confocal that guides only the reflected light from the point to the detecting means, and guides the numerical aperture of the optical system when the image is formed by the image sensor to the detecting means side. An endoscope characterized in that the numerical aperture is smaller than the numerical aperture of the optical system when light is emitted.

20. In additions 17, 18, and 19, the insertion part and the operation part are detachable. 21. In Additions 17, 18, and 19, the optical system provided in the insertion portion includes an objective optical system and a relay optical system that transmits light that forms an image by the objective optical system. 22. In additions 17, 18, and 19, the insertion portion is formed of a hard cylinder.

23. In Additions 17, 18, and 19, the first optical system and the second optical system have a first
Second diaphragm having an aperture larger than the diameters of the first diaphragm and the first diaphragm, and the first diaphragm and the second diaphragm at the pupil position of the objective optical system provided at the tip of the optical system provided in the insertion portion. It has a first and a second pupil imaging optical system which respectively connect the images of the diaphragms.

[0145]

As described above, according to the present invention, the illumination means, the optical system for forming an image of the illuminated subject, the image pickup means for picking up the formed image, the low interference light source, and the low interference light source. There is an optical system that guides the interference light to the subject and further guides the light reflected from the subject to the low interferometer, and signal processing means that constructs an image from the interference signal obtained from the low interferometer. The system and at least part of the optical system leading to the interferometer are the same, and the numerical aperture of the optical system focused on the image sensor is smaller than the numerical aperture of the optical system when light is guided to the low interferometer. This makes it possible to provide an optical system that can be placed in the endoscope insertion part, etc., and because it has such a numerical aperture, it is possible to obtain a normal macro image and a magnified observation image with high resolution due to low coherence light etc. To provide an easy-to-use optical imaging device. It can be.

[Brief description of drawings]

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

FIG. 2 is a configuration diagram showing an internal configuration of a control device.

FIG. 3 is a diagram showing a schematic configuration of a gimbal mirror.

FIG. 4 is a diagram showing a display example on a monitor.

FIG. 5 is a configuration diagram showing an internal configuration of a control device of a modified example.

FIG. 6 is an overall configuration diagram of an endoscope apparatus according to a second embodiment of the present invention.

FIG. 7 is an overall configuration diagram of an endoscope device according to a third embodiment of the present invention.

FIG. 8 is a diagram showing a configuration example of a double focus lens.

FIG. 9 is an overall configuration diagram of an endoscope device according to a fourth embodiment of the present invention.

FIG. 10 is an overall configuration diagram of an endoscope device according to a fifth embodiment of the present invention.

FIG. 11 is an overall configuration diagram of an endoscope device according to a sixth embodiment of the present invention.

FIG. 12 is a view of an insertion portion and an operation portion in a modified example as seen from a mounting portion.

FIG. 13 is an overall configuration diagram of an endoscope apparatus according to a seventh embodiment of the present invention.

FIG. 14 is an overall configuration diagram of an endoscope device according to an eighth embodiment of the present invention.

[Explanation of symbols]

1 ... Endoscopic device 2 ... Endoscope 3 ... Control device 4 ... Monitor 5 ... insertion part 6 ... Operation part 7 ... Fiber bundle 8 ... Light source device 9 ... Lamp 11 ... Illumination optical system 12 ... Subject 13 ... Objective optical system 15 ... Relay optical system 16 ... Half mirror 17a, 17b ... Pupillary imaging optical system 18a, 18b ... Aperture 19 ... Camera imaging optical system 20 ... Image sensor 22 ... CCU 23 ... Arithmetic circuit 24 ... Light source & detector 25 ... SLD 27a, 27b ... Optical fiber 28 ... Fiber coupler 30 ... Reference light side optical path adjusting mechanism 32 ... Stage 33 ... Mirror 35 ... Photodetector 37 ... Scanner driving device 39 ... Ginaval Scanner 41 ... Collimator optical system 42 ... Pupil diameter conversion optical system 43a, 43b ... Image of diaphragm

   ─────────────────────────────────────────────────── ─── Continued front page    (72) Inventor Yasuhiro Uehara             2-43 Hatagaya, Shibuya-ku, Tokyo Ori             Inside Npus Optical Industry Co., Ltd. F term (reference) 2G059 AA05 AA06 BB08 BB12 DD13                       EE02 EE09 EE11 FF02 FF03                       GG02 HH01 HH02 HH06 JJ11                       JJ13 JJ15 JJ17 JJ22 KK01                       KK03 KK04 MM09 PP04                 2H040 BA02 BA14 CA03 CA11 CA12                       CA22 CA26 DA02 GA02 GA11                 4C061 AA29 CC03 FF47 QQ07 WW04                       XX02

Claims (4)

[Claims] 1. An illuminating means, an optical system for forming an image of the illuminated object, an image pickup means for picking up the formed image, a low interference light source, and the low interference light to the object. There is an optical system that guides the reflected light to the low interferometer, and a signal processing unit that constructs an image from the interference signal obtained from the low interferometer. At least one of the optical system that forms the image of the subject and the optical system that guides the interferometer. An optical imaging apparatus having the same parts, wherein the numerical aperture of the optical system focused on the image sensor is smaller than the numerical aperture of the optical system when light is guided to the low interferometer. 2. An illuminating means, an optical system for forming an image of an illuminated object, an imaging means for picking up the formed image, a coherent light source, a confocal optical system, and coherent light from the confocal optical system. There is an optical system that guides light to the subject and further returns the reflected light from the subject to the confocal optical system, and a signal processing unit that constructs an image from the optical signal from the confocal optical system. And at least part of the optical system leading to the confocal optical system is the same, and the numerical aperture of the optical system focused on the image sensor is smaller than the numerical aperture of the optical system when light is guided to the confocal optical system. An optical imaging device characterized by the above. 3. An illuminating means, an optical system for forming an image of the illuminated object, an image pickup means for picking up the formed image, a low interference light source, and guiding the low interference light to the object and further reflecting from the object. There is an optical system that guides the generated light to the low interferometer and a signal processing means that constructs an image from the interference signal obtained from the low interferometer, and at least a part of the optical system that forms the image of the subject and the optical system that guides the interferometer. The optical imaging device is characterized in that the focal length of the optical system that forms an image on the image pickup element is longer than the focal length of the optical system when light is guided to the low interferometer. 4. An illuminating means, an optical system for forming an image of an illuminated object, an imaging means for picking up the formed image, a coherent light source, a confocal optical system, and coherent light from the confocal optical system. There is an optical system for guiding the reflected light from the subject to the confocal optical system and a signal processing means for constructing an image from the optical signal from the confocal optical system, and an optical system for forming an image of the subject. At least part of the optical system that guides the confocal optical system is the same, and the focal length of the optical system that forms an image on the image sensor is longer than the focal length of the optical system when light is guided to the confocal optical system. Characteristic optical imaging device.