JP2000126188A - Optical tomographic imaging apparatus - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide an optical tomographic imaging apparatus for obtaining a three-dimensional tomographic image of a diseased part. SOLUTION: A low interfering phototransmitting optical fiber 92 is passed through an endoscope 72 and the back end side of the fiber 92 is connected with the apex of a vibrating fiber 33a of an optically interfering part 76 and a light of an SLD 31 generating a low interfering light modulated through the fiber 33a is guided and the guided light is radially emitted around the central axis of an inserting part 78. The light reflected from an organ is emitted into the fiber 33a through the fiber 92 and a half of the light is transferred into a fiber 33b and is guided into an interfering light detecting part with a reference light reflected by a mirror 45. The light emitted from the fiber 33b is photoelectrically converted by a PD 53 and is stored into an image memory and when image data for one frame portion are obtd., they are outputted to a VP 106 and are converted into image signals and are outputted into a monitor through a superimposing circuit 91 and an optical tomographic image being superimposed on a CCD image is displayed.

Description

DETAILED DESCRIPTION OF THE INVENTION

[0001]

BACKGROUND OF THE INVENTION 1. Field of the Invention The present invention relates to an optical tomographic imaging apparatus for obtaining a tomographic image of a subject using low coherence light.

[0002]

2. Description of the Related Art Conventionally, in order to diagnose cervical cancer, the surface of the cervix is observed using a colposcope. In the colposcope, the degree of invasion in the depth direction of the lesion is estimated from the morphology of the surface of the cervix, or a biopsy is performed from the site that seems to be the most advanced, and it is determined by histological diagnosis,
He had decided on a treatment policy.

[0003]

However, in the above method, the correct diagnosis rate is poor (affected by the proficiency of the doctor or the site of the biopsy, etc.), and it is possible to survive after the treatment by transpiration or rounding with a laser. There is a problem that there is a possibility.

[0004] In addition, usually only one portion of a tissue is collected by biopsy, and there is a possibility that a diseased portion cannot be reliably collected. If a wide range of tissue is collected in order to surely collect a lesion, a large number of biopsies or a wide range of resections with a scalpel or the like is required, resulting in a disadvantage that patients suffer more.

[0005] The present invention has been made in view of the above points, and has as its object to provide an optical tomographic imaging apparatus capable of easily measuring the degree of infiltration of a lesion.

[0006]

In order to achieve the above object, an optical tomographic imaging apparatus according to the present invention comprises a low coherence light generating means for generating low coherence light, and an elongated insertion for insertion into a body cavity. And a light guide that guides low-coherence light generated by the low-coherence light generation means to the distal end of the insertion portion and guides light reflected by the subject. A light member, disposed in the insertion portion and at the tip side of the light guide member, deflects the optical axis of the low coherence light generated by the low coherence light generation means, and converts the low coherence light into A deflecting means for transmitting the light through the insertion portion and emitting the light; a light emitting scanning means for scanning the light emitting position on the subject by controlling the deflecting means; a reflected light guided by the light guide member and the low interference Interferes with the reference light generated from the Interference light extraction means for extracting an interference signal to be transmitted, light propagation time changing means for changing the light propagation time on the reference light side or reflected light side, and signal processing for the interference signal, and the light propagation time change means And a signal processing means for constructing a tomographic image in the depth direction of the subject, whereby the range of the lesion portion can be easily known from the tomographic image.

[0007]

Embodiments of the present invention will be described below with reference to the drawings. 1 to 3 relate to a first embodiment of the present invention, FIG. 1 shows an optical tomographic imaging apparatus of the first embodiment, FIG. 2 shows a configuration of a scanning unit, and FIG. , Indicating that a tomographic image is displayed.

The optical tomographic imaging apparatus 1 according to the first embodiment includes a colposcope 2 capable of observing an affected part 3 of a living body such as cervical cancer, and a colpososcope 2 which generates low coherence light for performing optical tomographic imaging. An optical tomographic image observation device 4 for guiding the light to the scope 2 side and causing the reflected light from the affected part 3 side to interfere with the reference light as the measurement light for detection, and an interference signal detected by the optical tomographic image observation device 4 , A signal processing device 6 for performing signal processing and the like for the TV camera 5 attached to the colposcope 2, and a monitor 7 for displaying a video signal output from the signal processing device 6. The (obverse) observation image of the diseased part 3 obtained by the TV camera 5 and the optical tomographic image by the light of low coherence are superimposed and displayed.

The colposcope 2 is a binocular, and a common objective lens 11 having a large diameter is attached to the distal end of the lens barrel 8 to form an optical image of the affected part 3 illuminated by illumination light (not shown). The variable power lenses 12a12b and the beam splitter 1 face the objective lens 11.
3a, 13b, imaging lenses 14a, 14b, and eyepieces 15a, 15b are arranged on respective optical axes.

The light split by the beam splitter 13a forms an image on a CCD (not shown) of the TV camera 5 via an imaging lens 16. The output signal of the TV camera 5 is input to a video signal processing circuit 17, where a video signal is generated and mixed by a superimposing circuit 18 with a video signal that has passed through a computing device 19 from the optical tomographic image observation device 4 side. Is output to the monitor 7, and displayed on the monitor 7, for example, as shown in FIG.

The other beam splitter 13b is a scanning unit 2
1, the light from the optical tomographic image observation apparatus 4 side is incident, and the light reflected on the affected part 3 side is reflected by the beam splitter 13
Through b, the light is guided to the optical tomographic image observation apparatus 4 side. The scanning unit 21 two-dimensionally scans the light with low coherence by the two-axis control unit 22.

An ultra-bright light emitting diode (hereinafter abbreviated as SLD) 31 as a light source for generating light having low coherence is arranged in the optical tomographic image observation apparatus 4. This SLD
Reference numeral 31 denotes a wavelength of, for example, 830 nm and, for example, a coherence length of about several tens to several thousand μm. This light is converted into linearly polarized light having a predetermined polarization plane through a lens 32a, a polarizer 32b, and a lens 32c, and is converted into a single mode. The light enters from one end face of the optical fiber 33a and is transmitted to the other end face (referred to as a tip face).

The optical fiber 33a is a PANDA on the way.
The other single mode optical fiber 33b is connected to the coupler 34.
And optically coupled. Therefore, this coupler 34
It is split into two parts and transmitted. Optical fiber 33a
(From the coupler 34) is wound around a piezoelectric element such as a ceramic (abbreviated as PZT) 35 of lead zirconate.

A driving signal is applied to the PZT 35 from an oscillator 36 to form a modulator 37 for modulating light transmitted by vibrating the optical fiber 33a. The frequency of this drive signal is, for example, 5 to 20 KHz. The modulated light is emitted from the distal end surface of the optical fiber 33a to the scanning unit 21.

As shown in FIG. 2, a condensing lens 38 is disposed in the scanning section 21 so as to face the distal end face of the optical fiber 33a, and the light enters a mirror 39 via the condensing lens 38. The mirror 39 is attached to the shaft of a first gear box 41b provided on the shaft of the first motor 41a, and is rotated by the first motor 41a controlled by the two-axis control unit 22 as shown by the arrow Y1. Is rotated.

The first motor 41a and the first gear box 41b are supported by a supporting member 41c, and the supporting member 41c is a second gear box disposed so as to be orthogonal to the axis of the first motor 41a. It is attached to a 41d shaft. The second gear box 41d is provided on a shaft of the second motor 41e.

When the second motor 41e controlled by the two-axis controller 22 is rotated, the mirror 39 is rotated as indicated by an arrow Y2. When the mirror 39 is rotated as indicated by arrows Y1 and Y2, the light that is two-dimensionally scanned toward the beam splitter 13b is guided, and the reflected light from the beam splitter 13b is transmitted to the end surface of the optical fiber 33a. To light.

As shown in FIG. 1, the beam splitter 13b
The light guided to the side is the variable power lens 12b and the objective lens 11
Is emitted to the affected part 3 side, the affected part 3 is two-dimensionally scanned, and a part of the light reflected by the internal tissue or the like of the affected part 3 is guided to the distal end surface of the optical fiber 33a via the beam splitter 13b. You.

About half of this light is transferred to the optical fiber 33b by the coupler 34, and is guided to the interference light detector 44. The optical fiber 33 b also transmits the light reflected by the mirror 45 attached to the distal end surface thereof (reference light obtained by splitting the light from the SLD 31 side by the coupler 34) and guides the light to the interference light detection unit 44. That is, the light guided to the interference light detection unit 44 side is transmitted to the optical fiber 33a side, and the measurement light reflected by the affected part 3 and the reference light reflected by the mirror 45 are mixed.

The mirror 4 in the optical fiber 33b
The optical path length of the optical fiber 33a wound by the modulator 37 is provided between the coupler 34 and the tip end to which 5 is fixed,
A compensation ring 46 for substantially compensating for the optical path length reaching the affected part 3 is provided. The light emitted from the rear end face of the optical fiber 33b is converted into a parallel light flux by the lens 47, and
After the light component on the polarization plane is extracted by the
At 9, the light is split into transmitted light and reflected light.

The reflected light is reflected by a mirror 51, and is condensed by a lens 52 (and a light component transmitted by a half mirror 49).
(Abbreviation) 53. The light transmitted through the half mirror 49 is reflected by the mirror 55 attached to the X-stage 54, and the light component reflected by the half mirror 49 is further condensed by the lens 52 and received by the PD 53. The X-stage 54 includes, for example, a stepping motor 56.
Is moved in the direction X facing the end face of the optical fiber 33b, so that the optical path length can be changed.

When obtaining an optical tomographic image of the affected part 3,
The optical path length until the light reflected by the mirrors 45 and 55 is incident on the PD 53, and the optical path length until the light returned from the affected part 3 through the optical fiber 33a is reflected by the mirror 51 and incident on the PD 53. Are set to be almost equal.

That is, by changing the position of the mirror 55 to change the optical path length on the reference light side, the optical path length on the measurement light side, which is equal to the optical path length on the reference light side, changes in the depth direction of the affected part 3. . Then, these two lights having almost the same optical path length interfere with each other and are detected by the PD 53.

The optical path length between the half mirror 49 and the mirror 51 and the optical path length between the half mirror 49 and the mirror 55 are set so as to always deviate at least from the interference range of the low coherent light. If the light is mixed by the half mirror 49 after the light itself is split into the transmitted light and the reflected light by the half mirror 49, interference is not caused.

The drive signal of the oscillator 36 or a signal having the same phase as the drive signal of the oscillator 36 is input to a lock-in amplifier or the like (not shown) of the arithmetic unit 19 constituting the signal processing device 6 together with the reference signal. A signal component having the same frequency as that of the reference signal in the signal from the PD 53 is subjected to heterodyne detection, and a signal component having the same phase is extracted and further detected and amplified. After that, it is input to a computer unit (not shown) inside the arithmetic unit 19.

The computer section has a scope by the colposcope 2 displayed on the monitor 7 as shown in FIG. 3A based on coordinate data indicated by the mouse 57 and a magnification signal input from the magnification detection circuit 58. The coordinates of the range of the cursor K superimposed on the image G1 are calculated.

From the calculation results of the coordinates, the rotation amounts of the motors 41a and 41e of the scanning unit 21 are determined.
, And optically scans the area designated by the mouse 57. The signal obtained by the optical scanning is temporarily stored in an image memory (not shown). When a predetermined range of a scanned image in the depth direction is obtained by scanning the mirror 55 by rotating the motor 56, the image data in the image memory is shown. The video signal is converted into a video signal corresponding to the optical tomographic image by the video signal processing unit, and is output to the monitor 7 via the superimposing circuit 18.

In this embodiment, when a video signal corresponding to an optical tomographic image is output from the arithmetic unit 19, the scope image G1 captured by the TV camera 5 is reduced, and FIG.
Are displayed simultaneously with the optical tomographic image G2.

According to this embodiment, the scope image G1 and the tomographic image G2 of the surface of the diseased part 3 such as the cervix can be displayed on the monitor 7 at the same time. It can be grasped from the tomographic image G2. For this reason, it is possible to determine the range of the lesion in the depth direction without having to perform the biopsy many times. Thus, the patient's distress can be reduced (since it is not necessary to perform multiple biopsies), and the burden can be reduced because the operator does not need to perform multiple biopsies.

The scanning section 2 is connected to the optical fiber 33a.
Since the light is guided to the colposcope 2 through 1, the diameter of the lens barrel 8 can be reduced. Also, the beam splitter 13b
Since the light is guided to the beam splitter 13b, a unitized structure detachable from the beam splitter 13b can be adopted. With this configuration, when the colposcope 2 is used, a unit for obtaining an optical tomographic image can be selectively used or not used as necessary.

FIG. 4 shows a TV according to a modification of the first embodiment.
6 shows a probe 61. In this modification, a TV probe 6 incorporating a CCD 62 is used instead of the colposcope 2 of FIG.
1 is used.

In the TV probe 61, an objective lens 64, a variable power lens 65, a dichroic mirror 66, an imaging lens 67, and a CCD 62 are sequentially arranged on a cylindrical probe body 63, and a signal of the CCD 62 is input to a video signal processing circuit 17. Is done. Further, the scanning unit 21 is attached to the reflection optical path side of the dichroic mirror 66 so as to guide the light of the optical fiber 33a to the dichroic mirror 66 and to guide the light from the dichroic mirror 66 to the optical fiber 33a. It has become.

As shown in FIG. 5, the dichroic mirror 66 has a reflectance intensity with respect to the wavelength of which the light in the near infrared region side from the vicinity of the boundary wavelength between the visible region and the near infrared region is almost one.
One that reflects 00% and transmits almost 100% of light in the visible region is used. The wavelength of the SLD 31 is set in the near-infrared region, is always reflected by the dichroic mirror 66, and does not adversely affect the CCD 62 that captures light in the visible region.

That is, the light from the optical fiber 33a is reflected by the dichroic mirror 66, guided to the objective lens 64, and the reflected light of the SLD 31 returning from the objective lens 64 to the dichroic mirror 66 is reflected by the dichroic mirror 66. The light is guided toward the optical fiber 33a. On the other hand, light in the visible region passes through the dichroic mirror 66 and forms an image on the CCD 62.

Other configurations are the same as those of the first embodiment. In this modification, the image displayed on the monitor 7 is observed without having the observation optical system with the naked eye in the colposcope 2 in the first embodiment. FIG. 6 shows an image G captured by the CCD 62 and displayed on the monitor 7.
A tomographic image can be observed on the monitor 7 only at a predetermined site (in this modified example, the center index S).

Therefore, the surgeon moves and sets the TV probe 61 so that the site desired to be observed is located at the center. The range of the tomographic image can be variably set within the scanning range of the two-axis controller 21. As shown in FIG. 7, a ring-shaped rubber 69 is attached in front of the objective lens 64 in FIG. 4, and the tip of the probe is pressed against a contactable part such as the cervix to obtain an optical tomographic image. You may do it.

FIG. 8 shows an optical tomographic imaging apparatus 71 according to a second embodiment of the present invention. The optical tomographic imaging apparatus 71 according to the second embodiment includes an endoscope 72 capable of observing an arbitrary part in a body cavity, a light source device 73 that supplies illumination light to the endoscope 72, and an endoscope 72 inside the endoscope 72. A light guide member for guiding light having low coherence provided is connected, and an optical interference device 74 for performing optical tomographic imaging and a monitor 75 as a display device for displaying an optical tomographic image by the optical interference device 74 are provided. Be composed.

The optical interference device 74 includes an optical interference unit 76 that obtains an electrical signal corresponding to the interference light for generating an optical tomographic image using the low-interference light, and converts the electrical signal of the optical interference unit 76 into a signal. A signal processing unit 77 for processing to generate a video signal corresponding to the optical tomographic image; this video signal is displayed on a monitor 75;

The endoscope 72 has an elongated and flexible insertion portion 78, and a wide operation portion 79 provided at the rear end of the insertion portion 78. The cable is extended from the outside.

A light guide 81 is inserted into the insertion portion 78, and a connector provided at the end of the light guide 81 on the cable side can be detachably attached to the light source device 73. By mounting, the white illumination light of the xenon lamp 82 inside the light source device 73 is condensed by the condenser lens 83 and supplied to the end of the light guide 81, and this illumination light is transmitted by the light guide 81 and inserted into the insertion section. 78 tip 8
The light is emitted to the side of the insertion section 78 from the other end face fixed to the illumination window provided on the side of the insertion section 78.

The illuminated light emitted from the side-view illumination window causes the illuminated site of interest, such as the luminal organ 85, to have its optical image formed by an objective lens 86 attached to the side-view observation window adjacent to the illumination window. Tied to its focal plane. A CCD 87 is arranged at the position of the focal plane, and photoelectrically converts the optical image.

The CCD 87 reads out the photoelectrically converted signal by applying a CCD drive signal from a CCD drive circuit 88, and outputs the read signal via a video signal line 89 to a video processor (hereinafter referred to as VP) as video signal processing means. Is written) 90.

The output signal of the VP 90 is output to the monitor 75 via the superimpose circuit 91,
To display the endoscope image taken.

The operating section 79 is provided with a bending operation mechanism (not shown). By operating a bending operation knob, the bending section formed at the rear end of the distal end portion 84 can be moved in any desired direction, up, down, left, or right. It can be bent. The endoscope 72 has an optical fiber 9 for transmitting light with low coherence.
2 has been inserted.

The distal end of the optical fiber 92 is fixed on the central axis of the distal end portion 84, and a gradient index lens (hereinafter referred to as a SELFOC lens) 93 is attached to the distal end surface. The rear end side of this optical fiber 92 is an optical interference section 76.
The light of the SLD 31 is guided through the optical fiber 33a.

The light of the SLD 31 enters through one end face of the single mode optical fiber 33a via the lens 32, and is transmitted to the other end face side. This optical fiber 33a is connected to the other single mode optical fiber 33 by a coupler 34 on the way.
b and is optically coupled. Therefore, this coupler 3
The signal is split into two parts in four parts and transmitted. Optical fiber 33
The front end side of a (from the coupler 34) is wound around a piezoelectric element such as PZT35.

The PZT 35 receives a drive signal from an oscillator 36 and forms a modulator 37 for modulating light transmitted by vibrating the optical fiber 33a. The modulated light is emitted from the distal end surface of the optical fiber 33a, is incident on the optical fiber 92 that contacts this distal end surface, and
The light is transmitted to the end face on the fourth side, and emitted from this end face via the selfoc lens 93.

A parallel beam is formed by a lens 94 disposed opposite to the SELFOC lens 93, reflected at right angles on a slope of a prism 96 attached to a gear 95, and emitted to the side of the insertion section 78. You. The gear 95 has an opening at a central portion thereof so that light can pass therethrough. The gear 95 is a gear 97a attached to the rotating shaft of the motor 97.
Is engaged.

Therefore, when the motor 97 rotates, the prism 96 is rotated, and the light guided by the optical fiber 92 is emitted radially around the central axis of the insertion section 78.

The motor 97 is fixed to a motor fixing base 98 having a rack formed on the back surface. This rack has a pinion gear 99a attached to the rotating shaft of the motor 99.
Is engaged.

When the motor 99 rotates, the rack moves, and the motor 97 fixed to the motor fixing base 98,
A gear 97a attached to the rotating shaft and a gear 95 maintaining the meshing state with the gear 97a move in the axial direction of the insertion portion 78, that is, in the longitudinal direction in conjunction therewith. The rotation amounts of these motors 97 and 99 are controlled by a position control device 101 in a signal processing unit 77.

The light reflected by the luminal organ 85 passes through a prism 96, a lens 94, and a selfoc lens 93 and is incident on the distal end surface of an optical fiber 92.
From the rear end face of the optical fiber 33a.
Almost half of this light is transferred to the optical fiber 33b by the coupler 34, and is guided to the interference light detection unit side together with the reference light reflected by the mirror 45 arranged opposite to the distal end surface of the optical fiber 33b.

In the first embodiment, the optical path length changing mechanism for changing the optical path length of the reference light is provided on the side of the interference light detecting section. In this embodiment, the optical path length changing mechanism is provided on the distal end surface of the optical fiber 33b. .

That is, the mirror 4 in the embodiment of FIG.
The reference numeral 5 is attached to the X-stage 54 and is moved by the motor 56 in a direction in which the optical path length of the reference light is changed, so that the optical path length is changed. Further, a lens 45a is arranged between the mirror 45 and the distal end surface of the optical fiber 33b. The rotation of the motor 56 is controlled by the position control device 101.

The light emitted from the rear end face of the optical fiber 33b is received by the PD 53 through the lens 52. PD53
Is amplified by the preamplifier 102 and then input to the signal input terminal of the lock-in amplifier 103 of the signal processing unit 77. A reference signal is input from the oscillator 36 to a reference signal input terminal of the lock-in amplifier 103.
Heterodyne detection and amplification are performed.

The output of the lock-in amplifier 103 is input to a computer 105 via a digital voltmeter (hereinafter abbreviated as DVM) 104 and corresponds to a tomographic image based on a signal obtained by light guided by the optical fiber 92. Control for generating image data is performed.

That is, a control signal is sent to the position control device 101 to control the amount of rotation of the motors 97 and 99, and to control the change in the optical path length by scanning the light beam and controlling the rotation of the motor 56. When scanning the light beam and changing the optical path length, the PD
The signal obtained from 53 is stored in a temporary image memory.

For example, when one frame of image data is obtained, the image data is output to the VP 106, which converts the VP 106 into a video signal, and outputs the video signal to the monitor 7 via the superimpose circuit 91.
5 and superimposed on the image of the CCD 87 so that an optical tomographic image is displayed.

Further, the motor 99 is rotated to rotate the prism 96.
Is moved in the longitudinal direction, the movement changes the optical path length on the measurement light side. Therefore, a control signal is sent to the position control device 101 and the motor 56 is rotated to compensate for the change in the optical path length. Control. With this control, image distortion due to a change in the optical path length is corrected. According to this embodiment, the advantage of the first embodiment can be obtained and a three-dimensional tomographic image can be obtained. The prism 9
Since 6 is inside the insertion portion 78, the prism 86 is not damaged.

FIG. 9 shows an optical tomographic imaging apparatus 111 according to a third embodiment of the present invention. The optical tomographic imaging apparatus 111 according to the third embodiment includes an endoscope 112 capable of observing an arbitrary part in a body cavity, a light source device 73 that supplies illumination light to the endoscope 112, and an endoscope 112. A light guiding member for guiding light having low coherence is connected, and an optical interference device 114 for generating light for optical tomographic imaging and detecting interference light is provided. A signal processing unit 115 performs signal processing such as generation of a video signal corresponding to an image, and a monitor 116 as a display device that displays a video signal output from the signal processing unit 115.

In the third embodiment, a dichroic mirror 117 is used to obtain a tomographic image of the living tissue 118 in the field of view of the endoscope.

As in the second embodiment, a light guide 81 is inserted into the insertion section 78 of the endoscope 112 to transmit the illumination light of the lamp 82 of the light source device 73, and the end of the endoscope 112 is fixed to the end 84. The front side of the living tissue 118 is illuminated from the surface through the glass plate 119 attached to the illumination / observation window. In this embodiment, the distal end side of the light guide 81 is configured to be branched into two.

An objective lens 86 is arranged inside the glass plate 119 and forms an image on the CCD 87. This CCD8
7 is driven by a CCD driving circuit 88, and a signal obtained by photoelectric conversion is supplied to a VP in a signal processing unit 115 through a video signal line 89.
The video signal input to the VP 90 and output from the VP 90 is input to the monitor 116 via the superimpose circuit 91. As shown in FIG. Is displayed.

A dichroic mirror 117 is disposed between the objective lens 86 and the CCD 87 and is inclined by 45 ° with respect to the optical axis of the objective lens 86. The dichroic mirror 117 has a characteristic as shown in FIG. 5, and transmits light in the visible region and reflects light in the near-infrared region. The prism 121 is arranged on the reflected light path of the dichroic mirror 117.

The prism 121 is mounted on a movable base 122 having a rack formed on the back surface. The tip of the optical fiber 92 is attached to the movable table 122 with an optical fiber fixing member, and the light emitted from the tip surface of the optical fiber 92 is reflected by the prism 121 and guided to the dichroic mirror 117 side. The light reflected by the dichroic mirror 117 is reflected by the prism 121 and guided so as to be incident on the distal end surface of the optical fiber 92.

The rack of the movable base 122 meshes with a pinion gear 125 attached to a tip of a shaft 124 connected to a rotating shaft of a stepping motor 123 housed in the operation section 79, for example, and the stepping motor 123 rotates. The movable table 122 is moved in a direction parallel to the optical axis of the objective lens 86, that is, in the longitudinal direction of the insertion section 78.

For example, when the movable base 122 is moved backward from the state shown in FIG. 9, the prism 121 is also moved backward, so that the light reflected by the prism 121 is guided as shown by a dotted line. You. Therefore, by moving the prism 121, light is scanned in the vertical direction on the living tissue 118 side, and a tomographic image corresponding to this scanning direction can be obtained.

The rear end of the optical fiber 92 is the optical interference device 1
14 is connected to the distal end face of the optical fiber 33a, and the SLD3
1 is guided to the optical fiber 92 side, and the reflected light from the optical fiber 92 side is transmitted to the optical fiber 33.
Light is guided to the a side.

In the optical interference device 114, the output of the PD 53 is input to the lock-in amplifier 103, and a signal component having the same phase as the reference signal is extracted and detected.
5 is input to the computer 126.

The computer 126 controls the rotation of the stepping motor 123 and the rotation of the motor 56.
Further, a process of generating a video signal corresponding to the tomographic image is performed,
By outputting to the superimpose circuit 91,
As shown at 0, a tomographic image is simultaneously displayed on the monitor 116 adjacent to the endoscope image.

Further, the computer 126 displays a cursor 128 indicating a region where a tomographic image is measured in the endoscope image as shown in FIG. This display makes it possible to know an area where a tomographic image can be obtained on an observation image, which is convenient for diagnosis. The cursor 128 can be deleted when it is unnecessary. In the configuration of the optical interference device 114, the same components as those of the optical interference unit 76 shown in FIG.

In this embodiment, a glass plate 119 that emits visible illumination light and captures visible observation light is provided on the distal end surface of the endoscope 112, and as shown in FIG.
The observation image can be obtained in a state where the distal end surface of the sample 8 is pressed against the tissue in the body cavity such as the inner wall 129 of the stomach.

Further, in a state of being pressed against the tissue in the body cavity,
Low-coherence light for obtaining an optical tomographic image is emitted through the glass plate 119 to the tissue in the body cavity, and the reflected light on the tissue in the body cavity can be taken in. A tomographic image for the central part can be obtained. By this close contact, blurring that occurs when the organ is moving or when the tip of the insertion portion 78 fluctuates can be prevented, and a clear observation image and tomographic image without blurring can be obtained. Therefore, in this embodiment, the observation system is set to a focal length suitable for observing the surface of the glass plate 119. The optical fiber 92 inserted through the endoscope 112 and the optical fiber 3 of the optical interference device 114
3a may be integrated.

FIG. 12 shows an optical tomographic imaging apparatus 131 according to a fourth embodiment of the present invention. The endoscope 132 according to the fourth embodiment differs from the endoscope 112 shown in FIG.
7, a front end surface of the image guide 133 is arranged, and an imaging lens 134 is arranged to face a rear end surface of the image guide 133. An image transmitted by the image guide 133 is converted by the imaging lens 134. The CCD 87 is arranged at the image forming position.

In this embodiment, the image guide 133 is inserted into the insertion section 78, the observation image is transmitted to the rear end face of the operation section 79, and the image is formed on the CCD 87 by the lens 134. The rest is the same as the configuration described in the third embodiment. In this embodiment, the endoscope image displayed on the monitor 116 is circular. Operation of this embodiment
The effects are almost the same as in the third embodiment. When the optical path length is changed, the optical path length is not limited to the reference light (reference light) serving as a reference.
The optical path length on the measurement light side may be changed. When an image of the surface of a subject such as a living body is obtained, the image is not limited to an image using visible light, and may be an image using infrared light, ultraviolet light, or the like.

[0076]

As described above, according to the present invention, there is an effect that the range in which the diseased tissue exists in the depth direction can be easily determined.

[Brief description of the drawings]

FIG. 1 is a configuration diagram showing an optical tomographic imaging apparatus according to a first embodiment of the present invention.

FIG. 2 is a perspective view illustrating a configuration of a scanning unit.

FIG. 3 is an explanatory view showing that a tomographic image is displayed together with an image of an affected part on a monitor.

FIG. 4 is a view showing a TV probe according to a modification of the first embodiment.

FIG. 5 is a characteristic diagram showing spectral characteristics of a dichroic mirror.

FIG. 6 is a view showing that an index corresponding to a range in which a tomographic image can be obtained is displayed on a monitor screen;

FIG. 7 is a sectional view showing a distal end side of a TV probe in a modification of FIG. 4;

FIG. 8 is a configuration diagram showing an optical tomographic imaging apparatus according to a second embodiment of the present invention.

FIG. 9 is a configuration diagram showing an optical tomographic imaging apparatus according to a third embodiment of the present invention.

FIG. 10 is a diagram showing an example of image display on a monitor.

FIG. 11 is a view showing that observation is possible in a state where the distal end surface of the insertion portion is pressed against tissue in a body cavity.

FIG. 12 is a configuration diagram showing an optical tomographic imaging apparatus according to a fourth embodiment of the present invention.

[Explanation of symbols]

 DESCRIPTION OF SYMBOLS 1 ... Optical tomographic imaging apparatus 2 ... Colposcope 3 ... Affected part 4 ... Optical tomographic image observation apparatus 5 ... TV camera 6 ... Signal processing apparatus 7 ... Monitor 8 ... Barrel 11 ... Objective lenses 12a, 12b ... Magnification lenses 13a, 13b ... Beam splitters 15a and 15b eyepiece 17 video signal processing circuit 18 superimposing circuit 19 arithmetic unit 21 scanning unit 22 biaxial control unit 31 SLD 32b polarizers 33a and 33b optical fiber 34 Coupler 35 PZT 36 Oscillator 37 Modulator 39 Mirror 41a, 41e Motor 44 Interference light detector 48 Analyzer 49 Half mirror 51, 55 Mirror 53 PD 54 X-stage 56 Stepping motor

 ──────────────────────────────────────────────────続 き Continuing on the front page (72) Inventor Shuichi Takayama 2-43-2 Hatagaya, Shibuya-ku, Tokyo Inside Olympus Optical Industrial Co., Ltd. (72) Inventor Kuniaki Kami 2-43-2 Hatagaya, Shibuya-ku, Tokyo Within Olympus Optical Co., Ltd. (72) Inventor Oka ▲ zaki ▼ Tsugio Students 2-43-2, Hatagaya, Shibuya-ku, Tokyo Inside Olympus Optical Co., Ltd. (72) Inventor Tetsumaru Kubota 2, Hatagaya, Shibuya-ku, Tokyo Chome 43-2, Olympus Optical Co., Ltd. (72) Koji Yasunaga 2-43-2, Hatagaya, Shibuya-ku, Tokyo (72) Inventor Atsushi Osawa 2 Hatagaya, Shibuya-ku, Tokyo (43) Inventor Kazushi Ohashi 2-43-2 Hatagaya, Shibuya-ku, Tokyo Orin Scan Optical Industry Co., Ltd. in the (72) inventor Daming Yoshinao Tokyo, Shibuya-ku, Hatagaya 2-chome No. 43 No. 2 Olympus Optical Industry Co., Ltd. in

Claims (3)

[Claims] A low-coherence light generating means for generating low-coherence light; an elongated insertion portion to be inserted into a body cavity; and a low-interference light generated by the low-coherence light generation device through the insertion portion. A light guide member that guides the active light to the distal end portion of the insertion portion and guides the reflected light reflected by the subject, and is disposed inside the insertion portion and at a distal end side of the light guide member, Deflecting means for deflecting the optical axis of the low coherence light generated by the low coherence light generating means, transmitting the low coherence light through the insertion portion and emitting the light, and A light emission scanning means for scanning a light emission position to the light source; and an interference signal corresponding to the interfered interference light by causing the reflected light guided by the light guide member to interfere with the reference light generated from the low coherence light. Interference light extracting means for extracting light, and changing the light propagation time on the reference light side or the reflected light side. Light propagation time changing means for performing the signal processing on the interference signal, and signal processing means for constructing a tomographic image in the depth direction of the subject by the light propagation time changing means. Optical tomographic imaging device. 2. An optical tomographic imaging apparatus according to claim 1, wherein said deflecting means is rotatable substantially coaxially with respect to an optical axis of said low coherence light. 3. The deflecting means is movable in substantially the same direction as the optical axis of the low coherence light.
Or the optical tomographic imaging apparatus according to claim 2.