JP3938705B2 - Optical imaging device - Google Patents

Description

[0001]
BACKGROUND OF THE INVENTION
The present invention relates to an optical imaging apparatus that obtains a high-resolution enlarged image together with a normal macro image using an endoscope or the like.
[0002]
[Prior art]
In recent years, endoscopes have been widely adopted in the medical field and the industrial field. In addition to a normal observation image obtained by an endoscope, in order to make a detailed diagnosis of whether or not a lesion is present, for example, in Japanese Patent Laid-Open No. 6-154228, an optical tomographic image can be obtained using low interference light. There is what I did.
[0003]
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 reduced in diameter.
[0004]
[Problems to be solved by the invention]
However, in the above conventional example, the numerical aperture (abbreviated as NA) of the objective optical system is the same value for the normal observation and for the optical tomographic image using the low interference light. There is.
[0005]
In other words, in normal usage, first, in a normal observation state, a wide area is observed macroscopically, and if there is a part that seems suspicious by such observation, a part of the part is optically tomographed. A method of examining the properties in detail by magnifying and observing with an image is adopted.
[0006]
In this case, the objective optical system is commonly used in the conventional example, and the NA thereof remains the same. For this reason, in a state suitable for normal observation, the resolution is insufficient in the state of the optical tomogram, and conversely, it is normal when the resolution is set to be high due to a large NA in the state of the optical tomogram. In the case of observation, a wide field of view cannot be secured, and only a narrow range can be observed.
[0007]
In addition, there is a conventional example that employs separate optical systems for macro observation and optical tomographic images. However, in the case of an endoscope inserted into a body cavity or the like as described above, a thin optical system is used. The diameter becomes difficult.
[0008]
In addition, when separate optical systems are used, the apparatus becomes large, and when a suspicious part is enlarged and observed with an optical tomographic image in an image for macro observation, the optical tomographic image is displayed in the macro image. Therefore, there is a drawback that the position to be enlarged and observed is likely to change with a change in distance or the like.
[0009]
(Object of invention)
The present invention has been made in view of the above-mentioned points, and a part of the optical system is made common so that it can be arranged also in an endoscope insertion portion or the like, so that the resolution by a normal macro image and low coherent light or the like is achieved. An object of the present invention is to provide an easy-to-use optical imaging apparatus capable of obtaining a high-magnification observation image.
[0010]
In addition, it can be arranged with a small diameter in the endoscope insertion section, and an optical imagen that can obtain a normal macro image and a magnified observation image with a high resolution by low coherence light or the like in a user-friendly state. Device To provide And the eyes Target.
[0011]
[Means for Solving the Problems]
An illuminating means, an optical system for imaging the illuminated object, and an imaging means for imaging the image formed;
A low-interference light source and an optical system that guides the low-interference light to the subject and further reflects the light reflected from the subject to the low-interferometer,
There is a signal processing means for constructing an image from the interference signal obtained from the low interferometer, and at least a part of the optical system that forms an image of the subject and the optical system that leads to the interferometer are the same, and the image is formed on the image sensor By making the numerical aperture of the optical system smaller than the numerical aperture of the optical system when light is guided to the low interferometer, it is possible to make an optical system that can also be arranged in an endoscope insertion section, and such numerical aperture. As a result, a normal macro image and an enlarged observation image with high resolution by low coherence light or the like can be obtained, and an optical imaging apparatus with good operability can be provided.
[0012]
DETAILED DESCRIPTION OF THE INVENTION
Embodiments of the present invention will be described below with reference to the drawings.
(First embodiment)
1 to 5 relate to a first embodiment of the present invention, FIG. 1 shows an overall configuration of an endoscope apparatus according to a first embodiment of the optical imaging apparatus of the present invention, and FIG. 2 shows a control apparatus. 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 modification.
[0013]
As shown in FIG. 1, an endoscope apparatus 1 as a first embodiment that realizes an optical imaging apparatus of the present invention is connected to an endoscope 2 that can be inserted into a body cavity, and the endoscope 2. The control device 3 that supplies illumination light or the like to the endoscope 2 or performs image processing and control operations, etc., and a monitor that is connected to the control device 3 and displays an endoscopic image and a high-definition enlarged image 4.
[0014]
The endoscope 2 includes a rigid insertion portion 5 that is inserted into a body cavity, and an operation portion 6 that is formed with a large width at the rear end of the insertion portion 5 and is grasped by an operator. The outer cover of the insertion portion 5 is formed of a hard cylindrical tube, and a light guide member for transmitting illumination light or an optical system having a function of transmitting to the rear side as well as imaging as described below. Is arranged.
[0015]
In the endoscope 2, a fiber bundle 7 as a light guide for transmitting illumination light (specifically white light) for normal observation is inserted in the insertion portion 5 and the operation portion 6, and this fiber bundle. 7 extends from the operation unit 6 to the outside, and its end is connected to the control device 3.
[0016]
As shown in FIG. 2, the light source device 8 provided inside the control device 3 includes a lamp 9 that generates white light and a condenser lens 10 that condenses the light on the end face of the fiber bundle 7. 7 is transmitted through the fiber bundle 7, further spreads forward from the distal end surface fixed to the distal end portion in the insertion portion 5 via the illumination optical system 11, and is emitted. Illuminate the side.
[0017]
The fiber bundle 7 is branched into two in the operation unit 6, and is branched into two in the insertion unit 5, so that two illumination optical systems 11 are arranged so as to face the two tip surfaces. Yes. The fiber bundle 7 may be inserted into an annular shape in the insertion portion 5 as described in other embodiments described later.
[0018]
An objective optical system 13 is disposed at the center between the two illumination optical systems 11 at the distal end of the insertion section 5, and light that forms an image by the objective optical system 13 is a relay optical system disposed in the insertion section 5. 15 is transmitted (guided) so as to relay to the rear side. Although only one relay optical system 15 is shown in FIG. 1, the number may be increased according to the length of the insertion portion 5.
[0019]
The light transmitted so as to relay the image to the rear side by the relay optical system 15 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 sensor 20 via the first pupil imaging optical system 17a and the first diaphragm 18a, and further via the camera imaging optical system 19.
[0020]
The image formed on the image sensor 20 is photoelectrically converted and input to a camera control unit (hereinafter abbreviated as CCU) 22 inside the control device 3 shown in FIG. The image signal component picked up by the image pickup device 20 is extracted by multiple sampling, and further subjected to color separation to generate a standard video signal, which is then sent to the arithmetic circuit 23.
[0021]
An image signal sent to the arithmetic circuit 23 (captured by the image sensor 20) is combined with an enlarged image, which will be described later, and output to the monitor 4. On the display surface of the monitor 4, for example, as shown in FIG. Twenty images 4a are displayed as endoscopic images.
[0022]
In the present embodiment, a light source & detection unit 24 that generates, for example, low-interference light and detects return light from the subject 12 side is provided inside the control device 3.
[0023]
The light source & detection unit 24 includes, for example, an ultra-bright light emitting diode (hereinafter abbreviated as SLD) 25 that generates low-coherence light. The low-coherence light from the SLD 25 is collected by a condenser lens 26. The light is incident on one end face of the optical fiber 27a. The optical fiber 27 a extends from the control device 3 to the outside, and the other end is fixed inside the operation unit 6 of the endoscope 2.
[0024]
The optical fiber 27 a is optically coupled to the other optical fiber 27 b at the fiber coupler portion 28 in the middle of the control device 3. Accordingly, the low-coherence light from the SLD 25 incident on the optical fiber 27a is transmitted to the other end surface on the operation unit 6 side, and is optically coupled by the fiber coupler unit 28 to form a reference-side optical path. The light also branches to the 27b side, and this light is modulated by a fiber modulator 29 formed by a piezo element or the like on the way.
[0025]
The fiber modulator 29 is driven by the arithmetic circuit 23 to modulate light guided by the optical fiber 27b. In addition, the optical path length side by the optical fiber 27a etc. from the fiber coupler part 28 to the operation part 6 side becomes a measurement side optical path length.
[0026]
The light transmitted through the fiber modulator 29 and transmitted through the optical fiber 27b is disposed opposite to one end face of the optical fiber 27b, and is disposed on the stage 32 by the collimator lens 31 forming the reference light side optical path length adjusting mechanism 30. The light enters the mirror 33 with a parallel beam and is reflected by the mirror 33.
[0027]
The light reflected by the mirror 33 passes through the fiber modulator 29 and is mixed with the return light on the optical fiber 27a side by the fiber coupler unit 28. In this case, if the difference in optical path length between the reference light side optical path length and the measurement side optical path length is within the coherence length of the low coherence light by the SLD 25, it becomes interference light, and is greater than or equal to the coherence length of the low coherence light. Does not interfere.
[0028]
The light mixed by the fiber coupler unit 28 is collected by the condenser lens 34 from the other end face of the optical fiber 27 b and received by a photodetector (abbreviated as PD in FIG. 2 and the like) 35.
[0029]
As described above, since the optical fiber 27b is optically coupled to the other optical fiber 27a at the intermediate fiber coupler portion 28, the reflected light from the reference light side optical path length adjusting mechanism 30 is reflected at the other end face of the optical fiber 27a. The received return light is optically mixed by the fiber coupler unit 28. That is, the optical path length from the fiber coupler 28 to the reference light side optical path length adjustment mechanism 30 side is the reference side optical path length. 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 interference light.
Therefore, the detection unit in the light source & detection unit 24 has a function as an interferometer.
[0030]
The signal photoelectrically converted by the photodetector 35 is input to the arithmetic circuit 23. The arithmetic circuit 23 demodulates the signal detected by the photodetector 35 and extracts an interference light component.
[0031]
In addition, the arithmetic circuit 23 sends a control signal to the stage 32 by an instruction operation from the front panel unit of the control device 3 or a keyboard 36 connected to the control device 3, and moves the stage 32 as indicated by an arrow A. Thus, the position of the mirror 33 is changed so that the reference side optical path length can be changed.
[0032]
Further, a scanner driving device 37 is provided inside the control device 3, and this scanner driving device 37 drives a gimbal scanner 39 shown in FIG. 1 through a signal line 38. The scanner driving device 37 is connected to the arithmetic circuit 23.
[0033]
Then, the arithmetic circuit 23 demodulates and extracts the signal of the interference light component from the signal from the light detector 35, and A / D converts the signal to associate it with the optical scanning by the scanner driving device 37. And storing the two-dimensional image data of the tomographic image by low coherence light.
[0034]
As shown in FIG. 1, a collimator optical system 41 is arranged to face an end face fixed inside the operation unit 6 in the optical fiber 27a, and light emitted from the end face of the optical fiber 27a by the collimator optical system 41 is parallel. The beam is incident on a gimbal scanner 39 as a two-dimensional scanner driven by a scanner driving device 37. 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.
[0035]
A schematic configuration of the gimbal scanner 39 is shown in FIG.
The gimbal scanner 39 holds the mirror surface 39a at the central portion by the first hinge portion 39b so that it can tilt in the horizontal direction, for example, and is held outside the first hinge portion 39b by the first hinge portion 39b. The second hinge portion 39c orthogonal to the direction is held so as to be tiltable in the vertical direction, and the mirror surface 39a is tilted two-dimensionally by a magnetic or electrostatic drive mechanism by a scanner drive signal from the scanner drive device. The light incident by the collimator optical system 41 is scanned two-dimensionally.
[0036]
As shown in FIG. 1, the light reflected by the gimbal scanner 39 is converted into a parallel beam with a large diameter light beam by a pupil diameter converting optical system 42 comprising a pair of convex lenses. The pupil diameter converting optical system 42 is configured to enlarge the diameter of the light beam so that a gimbal scanner 39 having a small size can be adopted.
[0037]
This parallel beam is condensed by the second pupil imaging optical system 17b through the second diaphragm 18b, partially transmitted by the half mirror 16, and incident on the relay optical system 15, and this relay optical system. Then, the light enters the objective optical system 13 through 15, is condensed by the objective optical system 13, and is focused and irradiated on the subject 12 side.
[0038]
Then, the reflected light from the subject 12 is guided to the end face of the optical fiber 27a through the reverse path. A part of the return light transmitted from the subject 12 side transmitted by the optical fiber 27 a is branched by the fiber coupler 28 to the optical fiber 27 b side and received by the photodetector 35.
[0039]
In the present embodiment, as shown in FIG. 1, in the insertion portion 5, in addition to the illumination means (specifically, the fiber bundle 7 and the illumination optical system 11) that performs normal illumination, the object illuminated by this illumination means is provided. An objective optical system 13 that forms an image of the specimen 12 and a relay optical system 15 that transmits the optical image to the rear operation unit 6 are disposed.
[0040]
The objective optical system 13 and the relay optical system 15 have a configuration similar to that of a normal optical endoscope, but the light is branched into a reflected light side and a transmitted light side by a half mirror 16 inside the operation unit 6. A branching unit is provided. The branching unit guides the reflected light to the imaging unit that performs imaging for normal observation, and guides the low interference light to the subject 12 side to the transmitted light side. In addition, a low interference light side optical system that guides return light from the subject 12 side (to the detector 35 functioning as an interferometer) is disposed.
The branching means can obtain normal observation image information and low-interference light (scanning) enlarged image information.
[0041]
As described above, in the present 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) using low interference light. Thus, the insertion portion 5 can be reduced in diameter.
[0042]
In the present embodiment, the first pupil imaging optical system 17a, the first stop 18a having a small stop diameter, and the second pupil connection are arranged on each optical path branched by the half mirror 16 inside the operation unit 6. An image optical system 17b and a second diaphragm 18b having a large diaphragm diameter are respectively arranged so that the image 43a of the first diaphragm 18a and the image 43b of the second diaphragm 18b are connected to the pupil position of the objective optical system 13. Yes.
[0043]
That is, in FIG. 1, the image (aperture image) 43a of the first diaphragm 18a is an aperture image having a small size on the optical axis O as shown by the dotted line, whereas the image (aperture image) of the second diaphragm 18b. Reference numeral 43b indicates a large aperture image on the optical axis O as indicated by a solid line.
[0044]
The normal observation imaging device 20 has a numerical aperture (hereinafter abbreviated as NA) of the objective optical system 13 so that only the light passing through the opening portion of the image 43a of the first aperture stop 18a functions for imaging. ) Is substantially small, and for low-coherence light, high-resolution objective optics is collected so that light passing through a large aperture of the image 43b of the second aperture stop 18b is condensed. It functions as the NA of the system 13.
[0045]
In this embodiment, when low-coherence light is used, the NA is increased to achieve high resolution, and a small region at the central portion in the normal observation range can be enlarged and observed.
[0046]
Note that FIG. 1 shows an off-axis principal ray when low-coherence light is used with a long dotted line. In this case, the observation range of the subject 12 is an optical axis O indicated by a one-dot chain line (indicated by a long dotted line). This is a small range indicated by the principal ray. Since the gimbal scanner 39 is also scanned in the direction perpendicular to the paper surface of FIG. 1, it can be observed in a small size in the direction perpendicular to the paper surface.
[0047]
Further, by generating image data from a large number of intensity data of interference light components in accordance with the scanning of the gimbal scanner 39, a high-resolution and high-definition image can be constructed.
[0048]
On the other hand, for normal observation, the NA of the objective optical system 13 is made substantially small so that a wide area can be observed without darkening the peripheral side of the field of view (due to vignetting). An image can be formed on the image sensor 20 so that a good image can be easily obtained.
[0049]
Then, as shown in FIG. 4A, a normal image (macro image) 4a by the image sensor 20 and a (high definition) enlarged image 4b by low coherence light are displayed so as to be adjacent to each other. The observation range 4c of the enlarged image 4b when low coherence light is used is displayed at the center so that the observation range 4c of the enlarged image 4b can be easily understood from the normal image 4a.
[0050]
In addition, when the gimbal scanner 39 is driven one-dimensionally in the horizontal direction, for example, and the stage 32 of the reference light side optical path length adjusting mechanism 30 is scanned in synchronization, thereby scanning in the depth direction of the subject 12. It is also possible to obtain tomographic images.
[0051]
In this case, for example, as shown in FIG. 4B, the tomographic image 4d is displayed adjacent to the normal image 4a, and in this case, for example, a line 4e indicating the cross-sectional position in the tomographic image 4d is displayed on the normal image 4a side. To do. The gimbal scanner 39 is driven one-dimensionally in the vertical direction, not in the horizontal direction, and the stage 32 is scanned in synchronization with the gimbal scanner 39 so that the depth of the gimbal scanner 39 along the vertical direction with respect to the subject 12 is increased. A tomographic image obtained when scanning in the direction can also be obtained.
[0052]
The effect | action of this Embodiment by such a structure is demonstrated below.
When the control device 3 is turned on, the subject 12 side is illuminated with illumination light from the light source device 8, and the illuminated subject 12 is imaged by the objective optical system 13 that functions as a small NA, and the relay optical system 15. Is transmitted to the rear side.
[0053]
Then, the light is reflected by the half mirror 16, passes through the pupil imaging optical system 17 a, the stop 18 a, and the camera imaging optical system 19, and is imaged and photoelectrically converted. The output signal is converted into a video signal by the CCU 22 by the image pickup device 20, and is output to the monitor 4 through the arithmetic circuit 23, and is taken by the image pickup device 20 as shown in FIG. 4A or 4B. The normal image 4a is displayed.
[0054]
On the other hand, the low-coherence light emitted from the SLD 25 is collected and incident on the optical fiber 27a. A part of the light is branched to the optical fiber 27b side by the fiber coupler unit 28, and the light is transmitted to the reference light side. Go round the light path.
[0055]
The light guided to the distal end side of the optical fiber 27 a is emitted from the end face in the operation unit 6, converted into a parallel beam by the collimator optical system 41, and incident on the gimbal scanner 39. The gimbal scanner 39 is a scanner driving device 37. Thus, the tilting drive is performed two-dimensionally, and the reflected light is scanned two-dimensionally.
[0056]
The reflected light from the gimbal scanner 39 is enlarged in beam diameter through the pupil diameter converting optical system 42, and then passed through the second aperture stop 18b with a large beam diameter, through the pupil imaging optical system 17b and the half mirror 16, and through the relay optical system 15. Guided to the side. After passing through the relay optical system 15, the object optical system 13 condenses and irradiates the subject 12 with the object optical system 13 so that the substantially outer diameter of the object optical system 13 is an opening.
[0057]
The reflected light on the subject 12 side passes through the reverse optical path, and is collected and incident on the tip surface of the optical fiber 27a. The light is optically coupled to the optical path length on the reference light side and the coherence of the low coherence light by the fiber coupler unit 28. Light within the length is received by the photodetector 35 as interference light.
[0058]
The signal photoelectrically converted by the photodetector 35 is input to the arithmetic circuit 23, where the arithmetic circuit 23 scans two-dimensionally and demodulates so as to extract the interference light component modulated by the fiber modulator 29, A digital signal is converted by an internal A / D converter and a signal input in a time series is stored in a memory to generate two-dimensional image data.
[0059]
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 as shown in FIG. In addition, the image is displayed as a high-definition enlarged image 4b together with the normal image 4a from the image sensor 20.
[0060]
When a scan change instruction is input from the keyboard 36, the scanner driving device 37 generates a driving signal in a one-dimensional manner and transmits it through the signal line 38 to drive the scanner 39 in a one-dimensional manner. Further, the arithmetic circuit 23 reciprocates the stage 32 in synchronization with the scanner 39 to construct a tomographic image with a signal from the photodetector 35.
In this case, the tomographic image 4d is displayed on the display surface of the monitor 4 together with the normal image 4a by the image sensor 20, as shown in FIG.
[0061]
According to the present embodiment, a wide range of the subject 12 can be observed as a normal image as a normal endoscope, and a narrow area at the center is observed with high resolution by an enlarged image with low coherence light. You can also
[0062]
Next, a typical case of NA in the present 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 the length that can be resolved, and λ represents the wavelength of light to be used.
[0063]
For example, in the case of a macro image, one pixel is a pixel having a length of 4 μm when considered by the imaging device 20 in which 500 × 500 pixels are arranged in a square of 2 mm square. In this case, it suffices if the half length 2 μm can be resolved by the sampling theorem, and the wavelength λ is 0.5 μm near the center of the white light.
[0064]
In this case, equation (1) is
2 = 0.56 × 0.5 / NA
Thus, NA = 0.14.
[0065]
On the other hand, if a length r that can be decomposed as a micro image is required to be at least about 1 μm, equation (1) is
1 = 0.56 × 0.8 / NA
It becomes. Here, the wavelength λ is 0.8 μm near infrared light.
In this case, NA = 0.448 or more.
[0066]
Therefore, the NA in the case of a micro image is 0.448 / 0.14≈3 in the case of a macro image. That is, the NA in the case of a micro image is at least three times the NA of the macro image.
[0067]
According to the present embodiment, since the micro image enlarged by the low coherence light is displayed in a narrow region at the center of the macro image, the normal endoscopic diagnosis can be performed using the macro image. In addition, since a micro image with a high resolution of high NA can be enlarged and displayed at the center, it is possible to provide an environment in which diagnosis can be made in more detail at the cellular level.
[0068]
In this case, the observation with the macro image and the observation with the micro image are performed using the common objective optical system 13 in a state in which the NA is substantially different. Therefore, the position where the micro image is observed in the macro image. However, it becomes invariable within a predetermined range of the central portion, and positioning when observing with a micro image becomes easy.
[0069]
Further, in the present embodiment, the objective optical system 13 and the relay optical system 15 are inserted into the insertion portion 5 in the same manner as a normal endoscope, and the optical system is also used in the case of low coherence light. Since it is set as the structure which carries out, the insertion part 5 can be reduced in diameter.
Therefore, the insertion part 5 of this Embodiment can be inserted with a small insertion hole, and the pain given to a patient can be reduced.
[0070]
In the above description, the case where low coherence light is used has been described. However, the present embodiment can be similarly applied to the case where a confocal optical system is used.
[0071]
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 in FIG.
[0072]
In this case, a light source & detection unit 24B having a simpler configuration is employed instead of the light source & detection unit 24 of FIG. For example, light from a laser diode 45 as a light source is collected by a condenser lens 46 and is incident on one end of an optical fiber 27a. The light is transmitted through the optical fiber 27a, and the other end face inside the operation unit 6 shown in FIG. The light is emitted from the (tip surface).
In this case, the size of the tip surface of the optical fiber 27a is sufficiently small and can perform the same function as a pinhole. In the same manner as described above, the light is condensed and irradiated with high NA from the objective optical system 13 to the subject 12 through the gimbal scanner 39 and the like.
[0073]
Then, only the reflected light from the focus position (focal point) of the objective optical system 13 follows the reverse optical path and is incident on the distal end surface of the optical fiber 27a, and the reflected light on the subject 12 side is other than the focal point of the objective optical system 13. Although there is a component in which the reflected light from the part returns through the objective optical system 13 or the like, they reach the periphery of the optical fiber 27a but do not enter the small end face of the optical fiber 27a.
[0074]
That is, the tip 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, light from other than the part in the conjugate relationship is excluded.
[0075]
The return light incident on the optical fiber 27 a is guided to the other optical fiber 27 c by the fiber circulator 47 provided in the light source & detector 24 B, and received by the photodetector 49 through the condenser lens 48.
[0076]
A signal photoelectrically converted by the photodetector 49 is input to the arithmetic circuit 23. The arithmetic circuit 23 performs almost the same process as that of the arithmetic circuit 23 shown in FIG. The image captured by the image sensor 20 by the CCU 22 is combined and a normal image 4a and a high-definition enlarged image 4b are displayed on the monitor 4 as shown in FIG.
This modification also has substantially the same effect as the first embodiment.
[0077]
(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. This endoscope apparatus 1 </ b> C includes an endoscope 2 </ b> C, a control device 3 (or 3 </ b> B), and a monitor 4.
[0078]
An endoscope 2C shown in FIG. 6 is the same as the endoscope 2 shown in FIG. 1, but the insertion portion 5 has the same configuration, 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. In this embodiment, the pupil imaging optical system 17 and the variable aperture 51 are arranged on a common optical path on the near side (relay optical system 15 side) that branches. .
[0079]
The variable diaphragm 51 is connected to, for example, the arithmetic circuit 23 inside the control device 3 or 3B by a signal line 52 so that the diaphragm diameter can be varied via the arithmetic circuit 23. For example, normally, a small aperture diameter 51a is set. In this state, when a normal image captured by the image sensor 20 is displayed on the monitor 4, and a switching instruction operation is performed from the keyboard 36 shown in FIG. The diameter 51b state is set. Along with the switching, the arithmetic circuit 23 displays a signal received by the photodetector 35 or 49, that is, an enlarged image (or tomographic image) by low coherence light or an enlarged image by the confocal optical system. To do.
[0080]
Other configurations are the same as those of the first embodiment. In the present embodiment, the variable diaphragm 51 is normally set in a state of a small diaphragm diameter 51a, and an observation similar to that of a normal endoscope can be performed. Then, for a portion that is desired to be magnified and observed, the arithmetic circuit 23 sets the variable aperture 51 to a large aperture diameter 51b state by setting the portion at the center of the observation field and performing a switching instruction operation. Then, an enlarged image (or tomographic image) by low coherent light or an enlarged image by a confocal optical system is displayed.
[0081]
In this embodiment, since the common optical system portion in the first embodiment is used more, the entire optical system can be reduced. Others have almost the same effect.
[0082]
Note that the size of the aperture diameter of the variable aperture 51 may be changed depending on the resolution, the observation range, and the like.
Specifically, when performing magnified observation (or tomographic image) using low-coherence light or magnified observation using a confocal optical system, the maximum resolution is determined by the maximum NA. When a wide range is to be observed, an instruction operation is performed from a keyboard or the like, thereby reducing the NA by the variable aperture 51 via the signal line 52 and wide scanning the two-dimensional scanning range by the gimbal scanner 39. In this case, a wide range can be set as the observation range, and at that time, by reducing the NA, the peripheral side may be observed with the same brightness as the central side.
[0083]
(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 apparatus 1D includes an endoscope 2D, a control device 3 (or 3B), and a monitor 4.
An endoscope 2D shown in FIG. 7 includes a bifocal lens 54 as the objective optical system 13 in the endoscope 2 of FIG.
[0084]
In the present embodiment, the tip surface of the optical fiber 27a, that is, the position where the light is emitted and the image forming surface is held by a two-dimensional scanner using a piezo element 55. The piezo element 55 is 56, and as shown by the solid line and the thick and long dotted line in FIG. It is possible to drive in a direction perpendicular to the paper surface.
[0085]
In the case of FIG. 7, the light from the tip surface of the optical fiber 27a passes through the imaging optical system 57, the second diaphragm 18b, and the second pupil imaging optical system 17b, and the relay optical system 15 on the front side of the half mirror 16 is used. Guide to the 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 includes a convex lens 57 and a diffractive lens 58 disposed in front thereof.
[0086]
The diffractive lens 58 has concavity and convexities formed concentrically, and the objective optical system 13 functions as a long focal length by focusing the normal observation light at the focal position Pa using zero-order light. On the other hand, the low-interference light or the light of the confocal optical system is focused at the focal position Pb using the first-order diffracted light, and in this case, the objective optical system 13 functions as a short focal length. I am doing so.
[0087]
As a representative example, the focal length when focusing on the focal position Pa is set to be three times or more the focal length when focusing on the focal position Pb using the first-order diffracted light (first embodiment). From the request for resolution, etc., similar to the case described in (1).
Other configurations are the same as those of the first embodiment.
[0088]
According to the present embodiment, in the case of normal observation, the objective optical system 13 having a long focal length and a small NA is caused to function. On the other hand, in the case of observation with low coherent light or a confocal optical system, the focal length is The objective optical system 13 is short and has a large NA and a high resolution.
[0089]
In the present embodiment, the distance at which the subject 12 is observed differs between normal observation and low-coherence light or a confocal optical system.
However, in the case of this embodiment, in the case of normal observation, the focal length is long and non-telecentric, so that observation over a wider range is easier than in the first embodiment. When a part of the image is to be enlarged and observed in detail, it can be enlarged and displayed as a micro image with low coherent light or a confocal optical system, thereby providing an environment in which diagnosis can be performed in more detail at the cellular level.
[0090]
Also in this embodiment, the insertion portion 5 is configured to be used in common for both normal observation and low coherence light or confocal optical systems, so that the insertion portion 5 can be reduced in diameter. .
[0091]
(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 apparatus 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. 1 except that the front lens as the objective optical system 13 is a liquid crystal lens 61 and the voltage application is turned on / off from the control device 3E via the signal line 62. The focal length can be changed by changing the refractive index.
[0092]
Further, in the present embodiment, the control device 3E has a configuration 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. 27a is not used.
[0093]
That is, the light from the laser diode 45 is collimated by the collimator lens 64, then partially transmitted by the half mirror 65, condensed by the condenser lens 66, and a pinhole formed at the focus position. The light passes through the pinhole of the element 67 and enters the collimator optical system 41.
[0094]
The collimated beam by the collimator optical system 41 is made to have a predetermined beam diameter by the second diaphragm 18b, then reflected by the gimbal scanner 39 and incident on the second pupil imaging optical system 17b, and further through the half mirror 16. Light is guided to the relay optical system 15 side.
[0095]
After being guided by the relay optical system 15, the liquid crystal lens 61 of the objective optical system 13 collects and irradiates the subject 12 with a short focal point. Then, the reflected light on the subject 12 side passes through the reverse path and enters the pinhole forming element 67. 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, and a part of the reflected light is reflected by the half mirror 65 and condensed by the condenser lens 68. The light is received by the photodetector 49.
[0096]
The signal from the photodetector 49 is amplified by the amplifier 69 and then input to the arithmetic circuit 23 in the control device 3E through the signal line 70.
Other configurations are the same as those of the first embodiment (modified example thereof).
[0097]
In the present embodiment, in the case of normal observation, the focal length of the objective optical system 13 is increased by reducing the refractive index of the liquid crystal lens 61, while the liquid crystal is used in the case of using the confocal optical system. The focal length of the objective optical system 13 is shortened by increasing the refractive index of the lens 61 or the like. For normal observation, the aperture 18a is set to a small NA, while when using a confocal optical system, the aperture 18b is set to a large NA for high resolution.
[0098]
In the present embodiment, normal observation and micro observation using a confocal optical system can be used in a time-division manner instead of simultaneous observation. The effect in this case is almost the same as that of the third embodiment.
[0099]
In the present embodiment, the light source & detection unit 24E is provided by a confocal optical system inside the operation unit 6, but the light source & detection unit 24 of FIG. 2 is provided inside the operation unit 6. Thus, the present invention can also be applied when low coherence light is used.
[0100]
(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 apparatus 1F includes an endoscope 2F, a control device 3 (or 3B), and a monitor 4.
[0101]
The endoscope 2F shown in FIG. 10 can be moved in the direction of the optical axis O in the endoscope 2 shown in FIG. I am doing so.
[0102]
In other words, the actuator 72 is connected to the arithmetic circuit 23 in the control device 3 (or 3B) by the signal line 73, and by performing a switching instruction operation from a keyboard or the like, the normal coherent light or the confocal optical can be used. The zoom optical system 71 can be set in the state of observation by the system.
[0103]
Specifically, the 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 at a position indicated by a dotted line in FIG. 10 in normal observation. The focal length of the optical system 13 becomes long.
[0104]
On the other hand, when an instruction for observation by low coherence light or a confocal optical system is given, the zoom optical system 71 is variably set from the state shown by the dotted line to the state shown by the solid line. In this case, the objective optical system The focal length of 13 is shortened.
[0105]
In this case, the focus is set at the same distance from the distal end surface of the insertion portion 5 as shown in FIG.
[0106]
Further, the configuration in the operation unit 6 in the endoscope 2F of the present embodiment is almost the same as that in the optical system in the operation unit 6 of the endoscope 2 in FIG. 1 except that the pupil diameter conversion optical system 42 is omitted. It has a configuration.
[0107]
Specifically, the light emitted from the front end surface of the optical fiber 27a is converted into a parallel beam by the collimator optical system 41, is made a predetermined beam diameter by the second diaphragm 18b, is incident on the gimbal scanner 39, and is reflected therefrom. The light is incident on the second pupil imaging optical system 17b without using the pupil diameter conversion optical system.
According to the present embodiment, although it is time-division, it is easier to widen the observation range for normal observation (macro image) than the first embodiment, as in the fourth and fifth embodiments. There is an effect that the observation distance between the macro image and the micro image can be made equal.
[0108]
(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 apparatus 1G includes an endoscope 2G, a control device 3 (or 3B), and a monitor 4.
[0109]
An endoscope 2G shown in FIG. 11 is configured such that the insertion unit 5 and the operation unit 6 are detachable from the endoscope 2 of FIG.
For this reason, 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.
[0110]
In this case, since the fiber bundle 7 is divided into two at the attachment portion 75 (on the insertion portion 5 side and the operation portion 6 side), in this embodiment, the fiber bundle 7 is diffused to the front end portion of the fiber bundle 7a on the operation portion 6 side. A plate 76 is provided, and illumination light is transmitted to the fiber bundle 7b on the insertion portion 5 side via the diffusion plate 76. And it branches into two inside the insertion part 5.
[0111]
Further, a second relay optical system 77 is disposed on the optical path between the relay optical system 15 in the insertion unit 5 and the half mirror 16 in the operation unit 6. In the second relay optical system 77, one convex lens 77a is disposed on the insertion portion side, and the other convex lens 77b is disposed on the operation portion 6 side. The paired lenses 77a and 77b allow the mounting portion 75 to emit light in a parallel beam. The light is guided.
[0112]
In the present embodiment, the tip of the optical fiber 27a is driven two-dimensionally by the piezo element 55 as shown in FIG. 7, for example, and the light emitted from the tip of the optical fiber 27a is the imaging optical system 57. Are collimated by the second aperture 18b, and are converged by the second pupil imaging optical system 17b. After passing through the half mirror 16, one of the second relay optical systems 77 is collected. The light is guided to the lens 77a on the insertion portion 5 side through the lens 77b.
The other configuration is the same as that of the first embodiment.
[0113]
In the present embodiment, since the insertion portion 5 is detachably attached to the operation portion 6, for example, the insertion portion 5 having a different length can be mounted and used.
[0114]
Therefore, it is possible to use an endoscope 2G having a different insertion portion length depending on a site to be used. In addition, the resolution can be changed to an appropriate one according to the site to be used, for example, by mounting the insertion portion 5 having a different focal length of the objective optical system 13 to increase the resolution. .
[0115]
Therefore, according to the present embodiment, in addition to the effects of the first embodiment, it can be used for a wider range of applications, and an observation image can be obtained in a state suitable for the intended use. .
[0116]
Although the present embodiment has been described in the case of a configuration similar to the first embodiment, for example, in the first embodiment, the insertion portion 5 and the operation portion 6 may be configured to be detachable. However, it can also be applied to other embodiments.
[0117]
FIG. 12A and FIG. 12B respectively show views of the insertion portion 5 and the operation portion 6 in the modification of the present embodiment as viewed from the attachment portion side.
[0118]
In this modification, a fiber bundle 7b is inserted into the insertion portion 5 in a ring shape inside a hard outer tube 81 of the insertion portion 5 as shown in FIG. A lens 77a (arranged in the vicinity of the relay optical system 15 and the rear end thereof) is attached to a lens tube (not shown).
[0119]
On the other hand, an annular attachment portion 82 is provided so that the rear end of the insertion portion 5 in the operation portion 6 is fitted and attached, for example, and an annular shape facing the fiber bundle 7b (on the insertion portion 5 side) inside thereof. A white LED 83 is disposed in the portion, and a lens 77b is disposed on the inner side thereof so as to face the lens 77a on the insertion portion 5 side.
This modification has substantially the same effect as that of the sixth embodiment.
[0120]
(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 a seventh embodiment of the present invention. The endoscope apparatus 1H includes an endoscope 2H, a control device 3 (or 3B), and a monitor 4.
[0121]
An endoscope 2H shown in FIG. 13 has a configuration in which the fiber bundle 7b provided in the insertion portion 5 and the illumination optical system 11 at the tip thereof are removed from the endoscope 2G in FIG. The illumination light emitted from the distal end surface of the fiber bundle 7a is collected by the illumination optical system 85, a part of the illumination light is reflected by the second half mirror 86, and the illumination light is guided to the second relay optical system 77 side. Like to do.
[0122]
In addition, the emission angle of the illumination light emitted from the distal end surface of the fiber bundle 7a is set to about the viewing angle when the image is formed on the imaging element 20, so that the imaging range can be illuminated efficiently. Other configurations are the same as those in FIG.
[0123]
According to the present embodiment, since the illumination light transmission means and the illumination optical system arranged in the insertion portion 5 can be made unnecessary, the insertion portion 5 can be reduced in diameter. The other effects are almost the same as those of the first embodiment.
[0124]
(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 apparatus 1I includes an endoscope 2I, a control device 3 (or 3B), and a monitor 4.
[0125]
The endoscope 2I shown in FIG. 14 is similar to the endoscope 2 shown in FIG. 1, for example, in the vicinity of the tip of the optical fiber 27a and on the gimbal scanner 39 side in the collimator optical system 41, the gimbal scanner 39, and the pupil diameter conversion optical system A lens (indicated by 42a) is disposed on the XY stage 91.
[0126]
The XY stage 91 is connected to the control device 3 (or 3B) (internal arithmetic circuit 23) via a signal line 92, and is two-dimensionally in the X and Y directions orthogonal to the optical axis O by an instruction operation from a keyboard or the like. To be able to move to.
[0127]
Until the first to seventh embodiments, the observation range by the low-coherence light or the confocal optical system is near a predetermined position of the central portion in the vicinity of the optical axis O in the observation range in the normal observation. In this embodiment, it is possible to move one-dimensionally in the X or Y direction or two-dimensionally in the X and Y directions so that the observation range by the low-coherence light or the confocal optical system can be changed. .
[0128]
It should be noted that the amount of movement by the XY stage 91 is detected by a detection means such as an encoder (not shown) so that the observation range by the low coherence light or the confocal optical system in that case can be known to the user by a frame or the like in the normal observation image. It may be displayed.
[0129]
Other configurations are the same as those of the first embodiment.
[0130]
In this embodiment, since the range to be magnified and observed can be moved and changed, the user can change and set the range to be magnified and observed so that the operability can be improved. The other operations and effects are the same as those of the first embodiment.
[0131]
Note that embodiments and the like configured by partially combining the above-described embodiments and the like also belong to the present invention.
[0132]
For example, in the eighth embodiment, the moving stage 91 is provided in the first embodiment. However, the moving stage 91 may be applied to other embodiments. Further, for example, in FIG. 11, the insertion portion 5 and the operation portion 6 are made detachable by the attachment portion 75, but the configuration of the insertion portion 5 and the operation portion 6 in that case is not the configuration shown in FIG. You may make it the structure of embodiment.
[0133]
[Appendix]
5). An illuminating means, an optical system for imaging the illuminated object, and an imaging means for imaging the image formed;
A low-interference light source and an optical system that guides the low-interference light to the subject and further reflects the light reflected from the subject to the low-interferometer,
There is 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 images the subject and the optical system that leads to the interferometer are the same, and the optical that forms an image on the image sensor An optical imaging apparatus characterized in that the object observation range of the system is wider than the object observation range of the optical system when guided to a low interferometer.
[0134]
6). An illuminating means, an optical system for imaging the illuminated object, and an imaging means for imaging the image formed;
A coherent light source, a confocal optical system, an optical system that guides coherent light from the confocal optical system to the subject, and returns reflected light from the subject to the confocal optical system;
There is a signal processing means that constructs an image from the optical signal from the confocal optical system, and at least a part of the optical system that images the subject and the optical system that leads to the confocal optical system are the same, and the image is formed on the image sensor. An optical imaging apparatus characterized in that the object observation range of the optical system is wider than the object observation range of the optical system when light is guided to the confocal optical system.
[0135]
7). An illuminating means, an optical system for imaging the illuminated object, and an imaging means for imaging the image formed;
A low-interference light source and an optical system that guides the low-interference light to the subject and further reflects the light reflected from the subject to the low-interferometer,
There is 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 images the subject and the optical system that leads to the interferometer are the same, and light is guided to the low interferometer. An optical imaging apparatus, wherein the diameter of the object observation range of the optical system is smaller than the diameter of the common optical system.
[0136]
8). An illuminating means, an optical system for imaging the illuminated object, and an imaging means for imaging the image formed;
A coherent light source, a confocal optical system, an optical system that guides coherent light from the confocal optical system to the subject, and returns reflected light from the subject to the confocal optical system;
There is a signal processing means that constructs an image from the optical signal from the confocal optical system, and at least a part of the optical system that images the subject and the optical system that leads to the confocal optical system are the same. An optical imaging apparatus, wherein a diameter of an object observation range of an optical system when light is guided is smaller than a common optical system.
[0137]
9. 3. The optical imaging apparatus according to claim 1, wherein the means for changing the numerical aperture has a diaphragm having a different aperture in each optical system.
10. 3. The optical imaging apparatus according to claim 1, wherein the means for changing the numerical aperture varies the aperture 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.
[0138]
12 5. The optical imaging apparatus according to claim 3, wherein the means for changing the focal length is to change a part of the optics.
13. 2. The optical imaging apparatus according to claim 1, wherein the numerical aperture of the optical system that forms an image of the subject on the imaging device is 1/3 or less of the numerical aperture of the optical system that guides light to the low interferometer.
14 3. The optical imaging apparatus according to claim 2, wherein the numerical aperture of the optical system that forms an image of the subject on the imaging element is 1/3 or less of the numerical aperture of the optical system that guides light to the confocal optical system.
[0139]
15. 4. The optical imaging apparatus according to claim 3, wherein a focal length of an optical system that forms an image of a subject on an imaging device is at least three times a focal length of an optical system that guides light to a low interferometer.
16. 5. The optical imaging apparatus according to claim 4, wherein a focal length of an optical system that forms an image of a subject on an imaging device is at least three times a focal length of an optical system that guides light to a confocal optical system.
[0140]
17. An illuminating means for illuminating the subject, an optical system for transmitting an image of the illuminated subject to the rear side in the insertion portion, and an endoscope that forms an image on an imaging element provided in the operation portion by the optical system; In an endoscope apparatus provided with 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.
A light branching means in the operation section;
A first optical system that forms an image of the optical system by the light branching unit, and a low-coherence light that is focused and irradiated on the subject side through the optical system; A second optical system for guiding light to the interferometer provided in the control device;
Provided,
An endoscope apparatus characterized in that the numerical aperture of the optical system when imaging is performed by the imaging device is made smaller than the numerical aperture of the optical system when light is guided to the interferometer side.
[0141]
18. In an endoscope in which an illuminating means for illuminating the subject and an optical system for transmitting an image of the illuminated subject to the rear side are provided in the insertion portion, and an image is formed on an imaging element provided in the operation portion by the optical system.
A light branching means in the operation section;
A first optical system that forms an image of the optical system on the imaging device by the light branching means, and a low coherence light is condensed and irradiated on the subject side through the optical system, and the reflected light is interfered. A second optical system for guiding light to the means for detecting light;
Provided,
An endoscope characterized in that the numerical aperture of the optical system in the case of forming an image with the imaging device is made smaller than the numerical aperture of the optical system in the case of guiding light to the interferometer side.
[0142]
19. In an endoscope in which an illuminating means for illuminating the subject and an optical system for transmitting an image of the illuminated subject to the rear side are provided in the insertion portion, and an image is formed on an imaging element provided in the operation portion by the optical system.
A light branching means in the operation section;
A first optical system for forming an image of the optical system by the light branching unit by the light splitting unit; and a focusing unit that irradiates and irradiates the subject side with the optical system and detects only reflected light from the condensing point. A second confocal optical system for guiding light to
Provided,
An endoscope characterized in that the numerical aperture of the optical system in the case of forming an image of the imaging element is made smaller than the numerical aperture of the optical system in the case of guiding light to the detection means side.
[0143]
20. In Additional Notes 17, 18, and 19, the insertion portion and the operation portion are detachable.
21. In Additional Notes 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 connects images by the objective optical system.
22. In Additional Notes 17, 18, and 19, the insertion portion is formed of a hard cylinder.
[0144]
23. In Additional Notes 17, 18, and 19, the first optical system and the second optical system each have a second diaphragm having an opening larger than a diameter of the first diaphragm and the first diaphragm, and the insertion First and second pupil imaging optical systems that connect the images of the first diaphragm and the second diaphragm to the pupil position of the objective optical system provided at the tip of the optical system provided in the section.
[0145]
【The invention's effect】
As described above, according to the present invention, the illumination unit, the optical system that forms an image of the illuminated object, the imaging unit that captures the formed image,
A low-interference light source and an optical system that guides the low-interference light to the subject and further reflects the light reflected from the subject to the low-interferometer,
There is a signal processing means for constructing an image from the interference signal obtained from the low interferometer, and at least a part of the optical system that forms an image of the subject and the optical system that leads to the interferometer are the same, and the image is formed on the image sensor. By making the numerical aperture of the optical system smaller than the numerical aperture of the optical system when light is guided to the low interferometer, it is possible to make an optical system that can also be arranged in an endoscope insertion section, and such numerical aperture. Therefore, an optical imaging apparatus with good operability can be provided so that a normal macro image and a magnified observation image with high resolution by low coherence light or the like can be obtained.
[Brief description of the 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 illustrating an internal configuration of a control device according to a modification.
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 apparatus according to a third embodiment of the present invention.
FIG. 8 is a diagram illustrating a configuration example of a bifocal lens.
FIG. 9 is an overall configuration diagram of an endoscope apparatus according to a fourth embodiment of the present invention.
FIG. 10 is an overall configuration diagram of an endoscope apparatus according to a fifth embodiment of the present invention.
FIG. 11 is an overall configuration diagram of an endoscope apparatus according to a sixth embodiment of the present invention.
FIG. 12 is a view of an insertion portion and an operation portion in a modification as seen from an attachment 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 apparatus according to an eighth embodiment of the present invention.
[Explanation of symbols]
1. Endoscope device
2. Endoscope
3. Control device
4 ... Monitor
5 ... Insertion section
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 ... Pupil imaging optical system
18a, 18b ... Aperture
19 ... Camera imaging optical system
20 ... Image sensor
22 ... CCU
23. Arithmetic circuit
24. Light source & detection unit
25 ... SLD
27a, 27b ... optical fiber
28 ... Fiber coupler
30: Reference light side optical path adjustment mechanism
32 ... Stage
33 ... Mirror
35. Photodetector
37 ... Scanner drive device
39 ... Ginaval scanner
41 ... Collimator optical system
42 ... Pupil diameter conversion optical system
43a, 43b ... Aperture image

Claims (2)

An illuminating means, an optical system for imaging the illuminated object, and an imaging means for imaging the image formed;
A low-interference light source and an optical system that guides the low-interference light to the subject and further reflects the light reflected from the subject to the low-interferometer,
There is a signal processing means for constructing an image from the interference signal obtained from the low interferometer, and at least a part of the optical system that images the subject and the optical system that leads to the interferometer are the same, and is imaged on the image sensor An optical imaging apparatus, wherein the numerical aperture of the optical system is smaller than the numerical aperture of the optical system when light is guided to the low interferometer. An illuminating means, an optical system for imaging the illuminated object, and an imaging means for imaging the image formed;
A low-interference light source and an optical system that guides the low-interference light to the subject and further reflects the light reflected from the subject to the low-interferometer,
There is 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 images the subject and the optical system that leads to the interferometer are the same, and the optical that forms an image on the image sensor An optical imaging apparatus characterized in that the focal length of the system is longer than the focal length of the optical system when light is guided to the low interferometer.

Images