JP2010051533A - Optical tomographic image reader - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To obtain a corresponding relationship between an endoscopic image and a tomographic image by OCT, and to diagnose a lesion correctly. <P>SOLUTION: This optical tomographic image reader, obtaining an optical tomographic image in the body cavity of a subject by using low-interference light, is characterized in that it has a probe obtaining the tomographic image in the body cavity by inserting through the forceps port of an endoscope in the body cavity of the subject and scanning the low-interference light rotatably and scanning to the rotary axial direction simultaneously, a means of obtaining the endoscopic image near the measured site of the probe imaged by the endoscope, a display means for displaying both of the tomographic image and the endoscopic image, a measuring range obtaining means for computing the measuring range of the probe from the endoscopic image, a display control means for overlapping the measuring range on the endoscopic image displayed by the displaying means and displaying, and a means for recording and storing the endoscopic image by responding to the tomographic image and the measuring range. <P>COPYRIGHT: (C)2010,JPO&INPIT

Description

  The present invention relates to an optical tomographic image reading apparatus, and more particularly, to an optical tomographic image reading apparatus that provides a correspondence between an endoscopic image and an OCT tomographic image at the time of OCT measurement using an OCT probe under an endoscope.

  Conventionally, an optical tomographic imaging apparatus using an optical coherence tomography (OCT) measurement method is known as a method for acquiring a cross-sectional image without cutting a measurement target such as a living tissue.

  This OCT measurement method is a kind of optical interferometry, in which light emitted from a light source is divided into measurement light and reference light, and the optical path length of the measurement light and reference light is within the coherence length of the light source. This is a measurement method using the fact that optical interference is detected only when the ranges match.

  Endoscopes, especially electronic endoscopes, have an illumination lens and a CCD image sensor at the tip of an insertion portion that is inserted into a body cavity, and white light from the illumination lens is observed in the body cavity. The image of the observed region is taken with a CCD image sensor. There is a method of acquiring an optical tomographic image by inserting an OCT probe from a forceps opening provided in an endoscope insertion portion as an OCT measurement method under an endoscope combining the endoscope and OCT. And optical tomographic images obtained by the OCT probe are respectively displayed on the monitor.

  Here, since the light used in the OCT measurement method is light that is not visible in the near infrared, it is difficult to confirm where the actual light hits the measurement site, so it is difficult to understand the correspondence between the optical tomographic image and the observation site image. There was a problem that it was difficult to diagnose.

  In contrast, for example, in an optical imaging apparatus that obtains an optical tomographic image of a living tissue using low-interference light, the pipe member having an optical fiber that transmits low-interference light therein is rotated and moved back and forth in the axial direction. Thus, it is known that a three-dimensional tomographic image is obtained or a tomographic image having a cross section in an arbitrary direction is obtained (see, for example, Patent Document 1).

  According to this, by displaying three-dimensionally, it is easier for a diagnostician to make a diagnosis than when only a two-dimensional image can be obtained from the image. Further, by displaying a three-dimensional imaging image, it becomes easy to quantitatively grasp the three-dimensional size of the affected part or the like.

  Further, for example, a tomographic image acquisition position line for acquiring a tomographic image is set on the observation image displayed on the display monitor, the observation image in which the tomographic image acquisition position line is set is associated with the color fundus image, and color It is known that the tomographic image acquisition position line is displayed on the fundus image so that the measurement position of the acquired tomographic image can be confirmed on the color fundus image (for example, Patent Document 2). Etc.).

According to this, the image obtained from the fundus camera and the tomographic image acquired by the fundus OCT are made to correspond to each other, and the position acquired by the OCT is displayed as a line on the fundus image, and the fundus image and the OCT tomographic image are displayed. The feature points of the image are extracted by image processing, and the fundus image and the OCT tomographic image are made to correspond to each other by matching the feature points of both.
JP 2000-321034 A JP 2007-117629 A

  However, in the one described in Patent Document 1, a three-dimensional image over the entire circumference can be obtained if the lumen is a small lumen such as a bile duct, but when a large lumen such as the large intestine or a space such as the stomach is large, Since a probe image can be obtained only within a narrow angle range, there is a problem that it is difficult to determine which part of the site observed by the endoscope is measured by OCT.

  Moreover, in what was described in the above-mentioned patent document 2, since the feature point of the image for which the correspondence of the image was acquired is extracted, it is difficult to cope with the image without the feature, and it is assumed that the OCT under the endoscope is temporarily performed. Even when applied to an apparatus, an OCT image obtained by a probe under an endoscope has a problem that it is difficult to extract and match features because the range obtained as an image is narrow.

  The present invention has been made in view of such circumstances, and provides an optical tomographic image reading apparatus capable of obtaining a correlation between an endoscopic image and a tomographic image obtained by OCT and performing a correct diagnosis of a lesioned part. The purpose is to do.

  In order to achieve the above object, an invention according to claim 1 is an optical tomographic image reading apparatus that obtains an optical tomographic image in a body cavity of a subject using low interference light, and is provided in an insertion portion of an endoscope. A probe that is inserted into the body cavity of the subject through a provided forceps port and that scans the low interference light in the body cavity and scans in the direction of the rotation axis to obtain a tomographic image in the body cavity Means for acquiring an endoscopic image in the vicinity of the measurement site of the probe imaged by the endoscope, display means for displaying both the tomographic image and the endoscopic image, and the endoscopic image Measurement range acquisition means for obtaining a measurement range in which the probe acquires the tomographic image; display control means for displaying the measurement range in an overlapping manner on the endoscopic image displayed on the display means; Endoscopic image, tomographic image and measurement range It provides an optical tomographic image reading apparatus characterized by comprising a recording means for recording stored in association.

  As a result, the position of the acquired tomographic image can be confirmed by the endoscopic image, and the correspondence between the endoscopic image and the tomographic image by OCT can be obtained, so that it is possible to correctly diagnose the lesioned part. Become.

  Moreover, as shown in claim 2, in the optical tomographic image reading apparatus according to claim 1, the measurement range acquisition unit has a wavelength different from that of the low interference light emitted from the probe. A means for emitting light as a measurement mark from the probe, and a light as the measurement mark are recognized on the endoscopic image, and a range irradiated with the light as the measurement mark is obtained by image processing. Means for obtaining on the endoscopic image.

  Thereby, by irradiating the light (aiming light) used as the mark of a measurement, the visibility of the site | part which carries out OCT measurement can be improved, and a measurement site | part can be confirmed easily.

  In addition, as shown in claim 3, in the optical tomographic image reading apparatus according to claim 1, the display means displays the tomographic image corresponding to an arbitrary position within the measurement range. And

  Thereby, the tomographic image of the part to be diagnosed can be easily displayed, and an accurate diagnosis can be performed.

  As described above, according to the present invention, the position of the acquired tomographic image can be confirmed by the endoscopic image, and the correspondence between the endoscopic image and the tomographic image by OCT can be obtained. It is possible to make a correct diagnosis.

  Hereinafter, an optical tomographic image reading apparatus according to the present invention will be described in detail with reference to the accompanying drawings.

  FIG. 1 is a block diagram showing a schematic configuration of an embodiment of an optical tomographic image reading apparatus according to the present invention.

  As shown in FIG. 1, the optical tomographic image reading apparatus 1 of the present embodiment includes an endoscope insertion portion 10 that is inserted into a body cavity 2 of a subject, a light source unit 12 that emits low-coherence light, A probe that guides the measurement light L1 split by the optical fiber coupler 14 that splits the light Lc emitted from the light source unit 12 into the measurement light L1 and the reference light L2 to the measurement target (observation unit) S in the body cavity 2 ( OCT probe) 16, an optical path length adjusting unit 18 that adjusts the optical path length of the reference light L2 divided by the optical fiber coupler 14, and from the measuring object S when the measuring light S1 is irradiated from the probe 16 to the measuring object S The interference light detection unit 20 that detects the interference light L4 obtained by combining the reflected light L3 and the reference light L2, and the frequency of the interference signal detected by the interference light detection unit 20 to analyze the measurement target S A processing unit (image acquisition unit) 22 that detects the intensity of the interference light L4 at each depth position and acquires a tomographic image of the measurement target S, and an endoscope apparatus that acquires an observation unit image in the body cavity 2 of the subject. And a display unit 26 that displays the acquired tomographic image and observation unit image, a control operation unit 28 that controls each unit, and the like.

The light source unit 12 emits the laser light La while sweeping the frequency at a constant period. Therefore, the light source unit 12 includes a light source 40 that emits light having a certain wavelength band, and a wavelength selection unit 41 that selects a wavelength emitted from the light source 40. The light source 40 includes a semiconductor optical amplifier (semiconductor gain medium) 42 that is connected to the optical fiber FB10 in a loop and emits spontaneous emission light and amplifies the spontaneous emission light guided from the optical fiber FB10. The light source 40 has a function of emitting spontaneous emission light to one end side of the optical fiber FB10 by injecting drive current and amplifying light incident from the other end side of the optical fiber FB10. When a drive current is supplied to the semiconductor optical amplifier 42, the laser light La is emitted to the optical fiber FB10 by a laser light source resonator formed by the semiconductor optical amplifier 42 and the optical fiber FB10.

  Next, the wavelength selection unit 41 selects a wavelength of spontaneous emission light guided from the optical fiber FB10 as a filter for a wavelength swept light source, and is an optical branching unit (circulator) coupled to the optical fiber FB10. Spontaneously emitted light is incident from 43 through the optical fiber FB11. The wavelength selection unit 41 includes a collimator lens 44, a diffraction grating element 45, an optical system (surface tilt correction lens) 46, a rotary polygon mirror (polygon mirror) 47, and the like.

  Light incident from the optical fiber FB11 is reflected by a rotating polygon mirror (polygon mirror) 47 via a collimator lens 44, a diffraction grating element 45, and an optical system 46. The reflected light is incident on the optical fiber FB11 again via the optical system 46, the diffraction grating element 45, and the collimator lens 44.

  The rotating polygonal mirror 47 rotates in the direction of the arrow R1 so that the angle of each reflecting surface changes with respect to the optical axis of the optical system 46. Thereby, only the light which consists of a specific frequency area among the lights disperse | distributed in the diffraction grating element 45 returns to the optical fiber FB11 again.

  The frequency of light returning to the optical fiber FB11 is determined by the angle between the optical axis of the optical system 46 and the reflecting surface. Light having a specific frequency range incident on the optical fiber FB11 is incident on the optical fiber FB10 from the optical splitter 43. As a result, laser light La having a specific frequency range is emitted from the optical fiber coupler 4 to the optical fiber FB1 side. It has become so.

  Therefore, when the rotary polygon mirror 47 rotates at a constant speed in the direction of the arrow R1, the wavelength of the light incident on the optical fiber FB11 is swept at a constant period. That is, the laser light La having the wavelength swept at a constant period is emitted from the light source unit 12 to the optical fiber FB 1 side through the optical fiber coupler 4.

  The light used in the OCT measurement method is light that is not visible in the near infrared, so it is difficult to confirm where the actual light hits the measurement site. Therefore, an aiming beam (aiming light) that serves as a mark for measurement is used. ) Is input together with the measurement light (OCT signal light).

  Therefore, the light source unit 12 includes an aiming light source 50 that emits aiming light Lb that is visible light for indicating a mark of measurement. The aiming light source 50 includes a semiconductor laser 48 that emits, for example, green or red laser light as the aiming light Lb, and a lens 49 that collects the aiming light Lb emitted from the semiconductor laser 48. Aiming light is emitted from the aiming light source 50 thus configured to the optical fiber FB2.

  The laser beam La guided by the optical fiber FB1 and the aiming light Lb guided by the optical fiber FB2 are combined by the optical fiber coupler 6. The light Lc obtained by combining the aiming light Lb and the laser light La is emitted to the optical fiber FB3 through the optical fiber coupler 6. Further, the light Lc is guided to the optical fiber coupler 14 by the optical fiber FB4 through the optical fiber coupler 8.

  The optical fiber coupler 14 is composed of, for example, a 2 × 2 optical fiber coupler, and divides the light Lc guided from the light source unit 12 through the optical fiber FB3 and the optical fiber FB4 into the measurement light L1 and the reference light L2. Is. The optical fiber coupler 14 is optically connected to the two optical fibers FB5 and FB7, so that the measurement light L1 is guided to the optical fiber FB5 side, and the reference light L2 is guided to the optical fiber FB7 side. It has become.

  An optical path length adjusting unit 18 is disposed at the tip of the optical fiber FB7.

  The optical path length adjustment unit 18 changes the optical path length of the reference light L2 in order to adjust the position at which tomographic image acquisition is started. The optical path length adjusting unit 18 reflects the reference light L2 emitted from the optical fiber FB7, the first optical lens 61 disposed between the reflective mirror 63 and the optical fiber FB7, and the first optical lens. And a second optical lens 62 disposed between the reflecting mirror 63 and the second optical lens 62.

  The first optical lens 61 has a function of converting the reference light L2 emitted from the optical fiber FB7 into parallel light and condensing the reference light L2 reflected by the reflection mirror 63 onto the core of the optical fiber FB7. . Further, the second optical lens 62 has a function of condensing the reference light L2 converted into parallel light by the first optical lens 61 onto the reflection mirror 63 and making the reference light L2 reflected by the reflection mirror 63 into parallel light. have.

  As a result, the reference light L2 emitted from the optical fiber FB7 becomes parallel light by the first optical lens 61 and is condensed on the reflection mirror 63 by the second optical lens 62. Thereafter, the reference light L2 reflected by the reflecting mirror 63 is converted into parallel light by the second optical lens 62, and is condensed by the first optical lens 61 on the core of the optical fiber FB7.

  Further, the optical path length adjustment unit 18 includes a movable stage 64 that fixes the second optical lens 62 and the reflection mirror 63, and a mirror moving mechanism 65 that moves the movable stage 64 in the optical axis direction of the first optical lens 61. Have. When the movable stage 64 moves in the direction of arrow A, the optical path length of the reference light L2 is changed.

  The light whose optical path length has been changed by the optical path length adjusting unit 18 enters the optical fiber FB7 again and is guided to the optical fiber coupler 14.

  On the other hand, the measurement light L1 split by the optical fiber coupler 14 and guided to the optical fiber FB5 side is inserted into the forceps port 15 of the insertion portion 10 of the endoscope via the optical connector OC. It is guided to the optical fiber FB6. The probe 16 is detachably attached to the optical fiber FB5 by the optical connector OC.

  The probe 16 is connected to the optical fiber FB5 via the optical connector OC, and the measurement light L1 guided by the optical fiber FB5 is incident on the optical fiber FB6 in the probe 16. The incident measurement light L1 is transmitted through the optical fiber FB6 and irradiated onto the measurement target S (the surface in the body cavity 2). Then, the return light (reflected light) L3 reflected by the measurement object S enters the optical fiber FB6, and thereby the inner wall section of the body cavity 2 is imaged.

  The reflected light L3 incident on the optical fiber FB6 is emitted from the optical fiber FB6 to the optical fiber FB5 via the optical connector OC.

  The reflected light L3 incident on the optical fiber FB5 is combined with the reference light L2 guided from the optical path length adjusting unit 18 through the optical fiber FB7 by the optical fiber coupler 14, and then interfered with the interference light L4, L5. Are output to the optical fiber FB8 and the optical fiber FB4, respectively. The interference light L4 enters the detector 30a via the optical fiber FB8, and the interference light L5 enters the detector 30b from the optical fiber coupler 8 via the optical fiber FB9.

  The interference light detection unit 20 detects interference light L4 and L5 generated by combining the reflected light L3 and the reference light L2 as interference signals. The interference light detection unit 20 has a function of adjusting the balance of the intensity of the interference lights L4 and L5 output from the optical fiber coupler 14 based on the detection results of the detectors 30a and 30b.

  From the interference signal detected by the interference light detection unit 20, the processing unit 22 is a region where the probe 16 and the measurement target S are in contact at the measurement position, more precisely, the surface of the probe outer cylinder of the probe 16 and the measurement target S. A region that can be considered to be in contact with the surface of the sensor is detected, and a tomographic image is acquired from the interference signal detected by the interference light detection unit 20.

  On the other hand, the optical tomographic image reading apparatus 1 of the present embodiment is connected to an endoscope apparatus 24 that acquires an observation part image (endoscopic image) in the body cavity 2 and can acquire the observation part image. ing.

  As described above, the insertion portion 10 of the endoscope includes the forceps port 15 that penetrates the insertion portion 10 and inserts the probe 16. The insertion unit 10 includes a CCD cable 71 and a light guide 72 extending to the tip.

  A CCD image sensor 73 is connected to the tip of the CCD cable 71. An illumination lens 74 is provided at the distal end portion of the light guide 72 so that the measuring object S is illuminated from the distal end portion of the insertion portion 10. In addition, an imaging lens 75 is provided at the distal end of the insertion unit 10, and a prism 76 is provided inside the imaging lens 75.

  The light guide 72 is connected to the endoscope device 24. The endoscope device 24 performs image processing of an image picked up by a white light source 78 that emits white light for image pickup of an observation unit through a lens 77 and a CCD image pickup device 73, and generates a generated image signal on the display unit 26. And an image processing unit 79 for outputting the data.

  The display unit 26 includes a monitor composed of a CRT, a liquid crystal display device, or the like, and displays a tomographic image and an observation unit image transmitted from the processing unit 22 and the image processing unit 79.

  The control operation unit 28 includes input means such as a keyboard and a mouse, and control means for managing various conditions based on the input information, and is connected to the processing unit 22, the image processing unit 79, the display unit 26, and the like. ing. The control operation unit 28 inputs, sets and changes various processing conditions in the processing unit 22 and the image processing unit 79 and changes the display setting of the display unit 26 based on an operator instruction input from the input unit. Is.

  As described above, in the present embodiment, the light Lc obtained by combining the low interference light (measurement light) La used for the OCT measurement with the light (aiming light) Lb serving as a mark for measurement of a visible wavelength different from this. The measurement light S and the aiming light Lb are coaxially scanned over the measurement target S, and an observation part image (endoscopic image) is captured by the CCD image pickup device 73 with white light, and the OCT tomographic image and the observation part image are obtained. The information is displayed on the display unit 26.

  Then, the aiming light irradiated on the measuring object S can be observed on the observation part image, and the site where the OCT measurement is performed can be accurately recognized.

  FIG. 2 shows an example of an OCT tomographic image and an observation unit image displayed on the display unit 26.

  In the example shown in FIG. 2, a small OCT tomographic image 80 and an observation part image (endoscopic image) 81 are displayed side by side in the upper right of the display screen. In the observation part image 81, a plurality of aiming lights 82 (trajectories) observed when the probe 16 is inserted into the body cavity 2 and the optical fiber FB6 is rotated and the probe 16 is scanned in the axial direction is displayed. Has been. At this time, the trajectory of the aiming light 82 indicating the measurement range for obtaining the tomographic image in the image processing unit 79 is synthesized on the observation unit image (endoscopic image), and the display on the display unit 26 is controlled by the control operation unit 28. The The scanning of the probe 16 in the axial direction is accurately performed by the control operation unit 28.

  As indicated by arrows in the figure, when one of the aiming lights 82a is designated, an OCT tomographic image at a position corresponding to the aiming light 82a is displayed as the OCT tomographic image 80.

  In addition, on the left side of the display screen, an OCT tomographic image 83 and an observation part image 84 are displayed large. The observation portion image 84 photographed by the CCD image pickup device 73 provided at the distal end of the insertion portion 10 of the endoscope is imprinted with the distal end portion 84a of the probe 16 and the aiming light 84b irradiated on the inner surface of the body cavity 2. It is rare. Further, the OCT tomographic image 83 is at a position corresponding to the irradiation position of the aiming light 84 b of the observation part image 84.

  Further, position information of the OCT measurement range is displayed in a frame indicated by reference numeral 85. Here, information indicating the start point and the end point in scanning in the axial direction of the probe 16 such as how many mm the endoscope has been inserted into the body and how many mm to how many mm the measurement range is pulled after that is displayed. . In the frame indicated by reference numeral 86, information such as patient, treatment, date, and other information, probe information, and the aiming light ON / OFF status are displayed.

  FIG. 3 shows a state of scanning by the probe 16.

  As shown in FIG. 3, the insertion portion 10 of the endoscope is inserted into the body cavity 2, the probe 16 is taken out from the distal end of the insertion portion 10 into the body cavity 2, and the optical fiber FB 6 is rotated in the probe 16 to rotate the body cavity 2. Take a tomographic image of the surface.

  At this time, as indicated by an arrow in the figure, the probe 16 is moved in the axial direction to capture tomographic images L1 (start), L2,..., Ln (end) at each position. These images L1, L2,..., Ln are two-dimensional tomographic images at each position, and a three-dimensional tomographic image can be obtained by combining these two-dimensional images.

  At the same time, an image of the observation part in the body cavity 2 including the position where the tomographic image is picked up by the OCT measurement is picked up by the CCD image pickup device 73 provided in the insertion part 10 of the endoscope. Aiming light is imprinted on the observation portion image picked up by the CCD image pickup device 73.

  FIG. 4 shows an example of such an observation part image.

  As shown in FIG. 4, aiming light 82 (trajectory thereof) indicating the position where each tomographic image L1, L2,. Here, the position of the left end aiming light is the start point of the probe axial direction scan corresponding to the tomographic image L1, and the position of the right end aiming light is the end point of the probe axial direction scan corresponding to the tomographic image Ln.

  The image processing unit 79 performs image analysis on the trajectory of the aiming light 82 and strictly obtains a scanning range (measurement range) from the start point to the end point.

  As described above, in the present embodiment, the feature of the image is not extracted and the image (the tomographic image and the observation portion image) is made to correspond, but the image acquisition position in the OCT measurement is obtained from another means using the aiming light and made to correspond. I am doing so. As a result, the position of the acquired OCT tomographic image can be confirmed by the observation part image (endoscopic image), and the correspondence between the observation part image and the tomographic image by OCT can be obtained. It becomes possible to do.

  Further, in the control operation unit 28, such a tomographic image (a two-dimensional tomographic image and a three-dimensional tomographic image as a set thereof) and an observation unit image are associated with the scanning range (measurement range) obtained in advance to be predetermined. Recorded in memory and saved.

  In the above-described embodiment, the image acquisition position in the OCT measurement is obtained from another means using the aiming light and is made to correspond. However, the confirmation of the position of the tomographic image is not limited to this, for example, A predetermined marking may be provided in the vicinity of the light emission of the probe 16, and this marking may be used as a Merckmar. That is, marking may be performed on a portion that appears in the observation part image at the tip of the probe 16, and the start point and end point of scanning may be obtained by image processing from the marking that appears in the observation part image. Moreover, it is not limited to marking, For example, it is good also considering a part with the characteristic of the member which comprises the probe 16 as a Merckmar.

  In addition, a measurement range based on the trajectory of the aiming light synthesized with the observation part image (endoscope image) and a three-dimensional tomographic image formed by combining the two-dimensional tomographic image are linked, and an arbitrary one of the measured ranges is selected. When a point is designated, a tomographic image corresponding to the position can be displayed.

  Although the optical tomographic image reading apparatus of the present invention has been described in detail above, the present invention is not limited to the above examples, and various improvements and modifications may be made without departing from the scope of the present invention. Of course.

1 is a block diagram showing a schematic configuration of an embodiment of an optical tomographic image reading apparatus according to the present invention. It is explanatory drawing which shows the example of the OCT tomographic image and observation part image which were displayed on the display part. It is explanatory drawing which shows the mode of the scanning by a probe. It is explanatory drawing which shows the example of the observation part image which imaged aiming light.

Explanation of symbols

  DESCRIPTION OF SYMBOLS 1 ... Optical tomographic image reading apparatus, 10 ... Endoscope insertion part, 12 ... Light source unit, 14 ... Optical fiber coupler, 16 ... Probe, 18 ... Optical path length adjustment part, 20 ... Interference light detection part, 22 ... Processing part , 24 ... Endoscopic device, 26 ... Display unit, 28 ... Control operation unit, 40 ... Light source, 41 ... Wavelength selection means, 42 ... Semiconductor optical amplifier, 43 ... Optical splitter (circulator), 44 ... Collimator lens, 45 DESCRIPTION OF SYMBOLS ... Diffraction grating element, 46 ... Optical system, 47 ... Rotary polygon mirror (polygon mirror), 50 ... Aiming light source, 61 ... 1st optical lens, 62 ... 2nd optical lens, 63 ... Reflection mirror, 64 ... Movable stage, 65 DESCRIPTION OF SYMBOLS ... Mirror moving mechanism, 71 ... CCD cable, 72 ... Light guide, 73 ... CCD image sensor, 74 ... Illumination lens, 75 ... Imaging lens, 76 ... Prism, 78 ... White light source, 79 ... Image processing Part

Claims (3)

An optical tomographic image reading device for obtaining an optical tomographic image in a body cavity of a subject using low interference light,
It is inserted into the body cavity of the subject through a forceps port provided in an insertion portion of the endoscope, and the low interference light is rotated and scanned in the body cavity in the body cavity. A probe for acquiring a tomographic image of
Means for acquiring an endoscopic image in the vicinity of a measurement site of the probe imaged by the endoscope;
Display means for displaying both the tomographic image and the endoscopic image;
From the endoscopic image, a measurement range acquisition means for obtaining a measurement range in which the probe acquires the tomographic image;
Display control means for displaying the measurement range in an overlapping manner on the endoscopic image displayed on the display means;
Recording means for recording and storing the endoscopic image, the tomographic image, and the measurement range in association with each other;
An optical tomographic image reading apparatus comprising:   2. The optical tomographic image reading apparatus according to claim 1, wherein the measurement range acquisition unit further transmits, from the probe, light serving as a measurement mark having a wavelength different from that of the low interference light emitted from the probe. Means for emitting, and means for recognizing the light serving as a marker of the measurement on the endoscopic image and obtaining a range irradiated with the light serving as the marker of the measurement on the endoscopic image by image processing; An optical tomographic image reading apparatus comprising:   2. The optical tomographic image reading apparatus according to claim 1, wherein the display unit displays the tomographic image corresponding to an arbitrary position within the measurement range.

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