JP5812785B2 - Optical tomographic image processing apparatus and method of operating optical tomographic image processing apparatus - Google Patents

Description

The present invention relates to an optical tomographic image processing apparatus and an operation method of the optical tomographic image processing apparatus . The present invention relates to an image processing technique capable of generating a corrected image from which liquid suspended matters are removed.

  In recent years, for example, in the medical field, optical coherence tomography (OCT) measurement has been used as a non-invasive method for obtaining tomographic information inside a living body. OCT measurement has an advantage that the resolution is about 10 μm higher than ultrasonic measurement, and detailed tomographic information (tomographic image) inside the living body can be obtained. In addition, it is possible to obtain tomographic information of a three-dimensional region by connecting the tomographic information acquired at a plurality of positions while shifting the position of acquiring the tomographic information.

  Currently, it is required to acquire detailed tomographic information of a living body for the purpose of cancer diagnosis and the like. As a method therefor, a time domain OCT (Time domain OCT) that obtains tomographic information on a subject by scanning light output from a low coherent light source has been proposed (Patent Document 1).

  Further, in recent years, an improved type that solves the problems that the optimum signal / noise ratio (S / N ratio), which is a disadvantage of the time domain OCT, cannot be obtained, the imaging frame rate is low, and the penetration depth (observation depth) is poor. The frequency domain OCT (Frequency domain OCT) which is OCT is utilized (patent document 2). Frequency domain OCT (Frequency domain OCT) is also used in diagnostic regions other than cancer and is widely used in clinical practice.

  As typical apparatus configurations for performing frequency domain OCT measurement, there are two types, that is, an SD-OCT (Spectral Domain OCT) apparatus and an SS-OCT (Swept SourceOCT). The SD-OCT apparatus uses broadband low-coherent light such as SLD (Super Luminescence Diode), ASE (Amplified Spontaneous Emission) light source, white light as a light source, and uses Michelson interferometer to generate broadband low-coherent light. After splitting into measurement light and reference light, irradiate the measurement light on the object to be measured, cause the reflected light and reference light that have returned at that time to interfere with each other, and decompose this interference light into frequency components using a spectrometer. Then, the interference light intensity for each frequency component is measured using a detector array in which elements such as photodiodes are arranged in an array, and the resulting spectrum interference intensity signal is Fourier-transformed by a computer. Information is acquired.

  On the other hand, the SS-OCT apparatus uses a laser that temporally sweeps the optical frequency as a light source, causes reflected light and reference light to interfere at each wavelength, and measures the time waveform of the signal corresponding to the temporal change of the optical frequency. The tomographic information is obtained by Fourier-transforming the spectral interference intensity signal thus obtained with a computer.

  In addition, the OCT apparatus can acquire three-dimensional information of the subject (measurement target) together with the tomographic information in the depth direction by scanning the optical axis of the measurement light two-dimensionally. By combining OCT measurement and three-dimensional computer graphic technology, it is possible to display a three-dimensional structure model composed of structure information of a measurement object having a resolution of the order of micrometers.

JP 2000-131222 A Special table 2007-510143 gazette

  By the way, in the OCT apparatus, when acquiring a tomographic image in the lumen of a living body, an optical probe containing an optical fiber with an optical lens and an optical mirror attached to the distal end is inserted into the lumen, and the distal end side of the optical fiber is inserted. Light is emitted into the lumen while performing radial scanning of the arranged optical mirror, and a tomographic image in the lumen is generated based on the reflected light from the tissue.

  When inserting an optical probe into a lumen, it is common to place a guide wire in the affected area in advance of the optical probe, and insert the probe to the affected area along the guide wire.

  As described above, in the OCT apparatus, since the measurement is performed with the optical probe and the guide wire inserted into the lumen, the optical probe and the guide wire appear in the tomographic image. In addition, liquid suspended matter (eg, bile mud in the bile duct) floating in the liquid in the lumen may appear in the tomographic image.

  These objects are not directly related to diagnosis and may interfere with diagnosis. As a result, it may lead to misdiagnosis and oversight of findings. For this reason, it is desirable to remove these objects from the tomographic image from the viewpoint of improving diagnosis efficiency and accuracy.

  However, among the objects appearing in the tomographic image, the liquid suspended matter in the lumen has an indeterminate shape, and the liquid suspended matter in the tomographic image is in comparison with an optical probe or guide wire having a defined shape. It is extremely difficult to specify the region or position, and there is a problem that complicated processing is required to remove the liquid suspended matter from the tomographic image.

The present invention has been made in view of such circumstances, and an optical tomographic image processing apparatus and an optical tomographic image that can easily provide a corrected image in which liquid suspended matters in a lumen are removed from a tomographic image. It is an object of the present invention to provide a method for operating a processing apparatus .

  In order to achieve the above object, an optical tomographic image apparatus according to the present invention includes an image acquisition means for acquiring an optical tomographic image in a lumen by optical coherence tomography, and is inserted into the lumen from the optical tomographic image. Luminal insert detection means for detecting a region of the luminal insert formed, luminal tissue detection means for detecting a tissue region of the lumen from the optical tomographic image, and the lumen from the optical tomographic image A liquid suspended matter detecting means for detecting a region of liquid suspended matter floating in the liquid in the lumen from the optical tomographic image by subtracting the region of the insert and the tissue region of the lumen; and the liquid Correction image generation means for generating a correction image in which the liquid floating substance is removed from the optical tomographic image based on the detection result of the floating substance detection means.

  In the optical tomographic imaging apparatus of the present invention, the luminal insert detection means can detect the region of the optical probe inserted into the lumen as the region of the luminal insert.

  Further, the lumen insert detection means can detect a region of a guide wire for guiding the optical probe into the lumen as the region of the lumen insert.

  Further, the corrected image generating means is a corrected image in which the luminal insert and the liquid suspended matter are removed from the optical tomographic image based on detection results of the lumen inserted matter detecting means and the liquid suspended matter detecting means. Can be generated.

  In addition, the correction image generation means includes an instruction means for selectively instructing whether or not to remove each region detected by the lumen insertion detection means and the liquid suspended matter detection means from the optical tomographic image. According to an instruction from the instruction means, a corrected image in which the luminal insert and the liquid suspended substance are selectively removed from the optical tomographic image can be generated.

  Moreover, it is preferable to provide a display means for displaying the corrected image generated by the corrected image generating means.

  The lumen can be a bile duct, pancreatic duct, blood vessel, or ureter.

In the operation method of the optical tomographic image processing apparatus of the present invention, the image acquisition means acquires an optical tomographic image in the lumen by optical coherence tomography measurement, and the luminal insert detection means detects the optical tomographic image. A lumen insert detecting step for detecting a region of the lumen insert inserted into the lumen from the inside, and a lumen tissue detecting means detects the tissue region of the lumen from the optical tomographic image A lumen tissue detecting step and a liquid suspended matter detecting means subtracting the lumen insertion region and the lumen tissue region from the optical tomographic image, thereby subtracting the intraluminal region from the optical tomographic image. A liquid floating substance detection step for detecting a region of the liquid floating substance floating in the liquid of the liquid, and a correction image generation means that detects the liquid floating substance from the optical tomographic image based on the detection result of the liquid floating substance detection step. Corrected image generator that generates the corrected image removed Characterized in that it comprises a and.

In the operation method of the optical tomographic image processing apparatus according to the present invention, the lumen insert detection means includes the lumen insert detection step in which the region of the optical probe inserted into the lumen is the tube. It can be detected as a region of the cavity insert.

Further, in the lumen insert detection step, the lumen insert detection means detects a region of a guide wire for guiding the optical probe into the lumen as the region of the lumen insert. it can.

Further, in the corrected image generation step, the correction image generation unit is configured to detect the lumen insert and the liquid floating from the optical tomographic image based on detection results of the lumen insert detecting step and the liquid floating matter detecting step. A corrected image from which objects have been removed can be generated.

Further, the instruction means includes an instruction step for selectively instructing whether or not to remove each region detected by the lumen insertion detection step and the liquid suspended matter detection step from the optical tomographic image, and the correction The image generation step can generate a corrected image in which the luminal insert and the liquid suspended matter are selectively removed from the optical tomographic image in accordance with an instruction of the instruction step.

The display means may include a display step for displaying the correction image generated by the correction image generation step.

  The lumen can be a bile duct, pancreatic duct, blood vessel, or ureter.

According to the optical tomographic image processing apparatus and the operation method of the optical tomographic image processing apparatus of the present invention, the region of the luminal insert or the tissue region of the lumen is detected from the optical tomographic image, and these regions are detected from the optical tomographic image. By subtracting, it is possible to detect the area of the liquid suspension in the lumen. Accordingly, it is possible to easily provide a corrected image in which the liquid suspended matter in the lumen is removed from the optical tomographic image. As a result, it is possible to provide a corrected image in which information not directly related to diagnosis is removed from the optical tomographic image, and it is possible to improve the efficiency and accuracy of diagnosis.

1 is an external view of an image diagnostic apparatus to which a tomographic image processing apparatus according to an embodiment of the present invention is applied. The block diagram which shows the internal structure of the OCT processor of FIG. Sectional view of the OCT probe of FIG. The figure which shows the scanning surface of a tomographic image in case optical scanning is radial scanning with respect to a measuring object The figure which shows the three-dimensional volume data constructed | assembled by the tomographic image of FIG. The figure which shows a mode that a tomographic image is acquired using the OCT probe derived | led-out from the forceps opening | mouth of the endoscope of FIG. The block diagram which shows the structure of the signal processing part of FIG. Schematic diagram showing the state when measurement is performed with an OCT probe inserted into the bile duct The flowchart figure which showed the flow of the process performed in the tomographic image correction | amendment part of FIG. The figure which showed an example of the tomographic image produced | generated from tomographic image data The figure which showed a mode that the inner wall surface (minimum cost path) of the OCT probe was detected in the probe area | region detection process. The figure which showed a mode that the outer wall surface (probe surface line) of the OCT probe was detected in the probe area | region detection process. The figure which showed the mode when a guide wire was detected in the detection process of a guide wire area The figure which showed the mode after a hysteresis binarization process was performed in the detection process of a luminal tissue area | region The figure which showed the mode when the binarized image was obtained in the detection process of a luminal tissue area | region The figure which showed a mode when bile mud was detected in the detection process of a liquid suspended solids area Figure showing an example of a corrected tomographic image

  Hereinafter, preferred embodiments of the present invention will be described in detail with reference to the accompanying drawings.

  FIG. 1 is an external view of an image diagnostic apparatus to which an optical tomographic image processing apparatus according to an embodiment of the present invention is applied. As shown in FIG. 1, the diagnostic imaging apparatus 10 mainly includes an endoscope 100, an endoscope processor 200, a light source device 300, an OCT processor 400 as a tomographic image processing apparatus, and a monitor device 500. Note that the endoscope processor 200 may be configured to incorporate the light source device 300.

  The endoscope 100 includes a hand operation unit 112 and an insertion unit 114 that is connected to the hand operation unit 112. The surgeon grasps and operates the hand operation unit 112 and performs observation by inserting the insertion unit 114 into the body of the subject.

  The hand operation part 112 is provided with a forceps insertion part 138, and the forceps insertion part 138 communicates with the forceps port 156 of the distal end part 144. In this embodiment, the OCT probe 600 is led out from the forceps opening 156 by inserting the OCT probe 600 from the forceps insertion portion 138. The OCT probe 600 is inserted into the OCT processor 400 via the insertion portion 602 inserted from the forceps insertion portion 138 and led out from the forceps opening 156, the operation portion 604 for the operator to operate the OCT probe 600, and the connector 610. It consists of a cable 606 to be connected.

  At the distal end portion 144 of the endoscope 100, an observation optical system 150, an illumination optical system 152, and a CCD (not shown) are disposed.

  The observation optical system 150 forms an image of a subject on a light receiving surface (not shown) of the CCD, and the CCD converts the subject image formed on the light receiving surface into an electric signal by each light receiving element. The CCD of this embodiment is a color CCD in which three primary color red (R), green (G), and blue (B) color filters are arranged for each pixel in a predetermined arrangement (Bayer arrangement, honeycomb arrangement). is there. Reference numeral 154 denotes a cleaning nozzle for supplying cleaning liquid and pressurized air toward the observation optical system 150.

  The light source device 300 causes visible light to enter a light guide (not shown). One end of the light guide is connected to the light source device 300 via the LG connector 120, and the other end of the light guide faces the illumination optical system 152. The light emitted from the light source device 300 is emitted from the illumination optical system 152 via the light guide, and illuminates the visual field range of the observation optical system 150.

  An image signal output from the CCD is input to the endoscope processor 200 via the electrical connector 110. The analog image signal is converted into a digital image signal in the endoscope processor 200, and necessary processing for displaying on the screen of the monitor device 500 is performed.

  In this manner, observation image data obtained by the endoscope 100 is output to the endoscope processor 200, and an image is displayed on the monitor device 500 connected to the endoscope processor 200.

  FIG. 2 is a block diagram showing an internal configuration of the OCT processor of FIG. The OCT processor 400 and the OCT probe 600 shown in FIG. 2 are for acquiring tomographic information (tomographic image) to be measured by an optical coherence tomography (OCT) measurement method.

  The OCT processor 400 emits light La for measurement, a first light source unit (first light source unit) 12, and the light La emitted from the first light source unit 12 is measured light (first light flux). An optical fiber coupler (branching / combining unit) 14 for branching into L1 and reference light L2 and combining the return light L3 and the reference light L2 from the measurement target S, which is the subject, to generate interference light L4; The measurement light L1 branched by the fiber coupler 14 is guided to the optical connector 18 of the OCT probe 600, and the fixed-side optical fiber FB2 that guides the return light L3 guided by the rotation-side optical fiber FB1 in the OCT probe 600; The interference light detection unit 20 that detects the interference light L4 generated by the optical fiber coupler 14 as an interference signal, and processes the interference signal detected by the interference light detection unit 20 to obtain tomographic information ( A signal processing unit 22 for acquiring layer image). The tomographic information acquired by the signal processing unit 22 is imaged and displayed on the monitor device 500.

  Further, the OCT processor 400 adjusts the optical path length of the second light source unit (second light source unit) 13 that emits aiming light (second light flux) Le for indicating a mark of measurement, and the reference light L2. Detection that detects return light (interference light) L4 and L5 combined by the optical fiber coupler 14 and optical fiber coupler 28 that splits the light La emitted from the first light source unit 12 Devices 30a and 30b, and an operation control unit 32 for inputting various conditions to the signal processing unit 22, changing settings, and the like.

  The OCT probe 600 connected to the OCT processor 400 guides the measurement light L1 guided through the fixed optical fiber FB2 to the measurement target S and also guides the return light L3 from the measurement target S. An optical fiber FB1 and an optical connector 18 that rotatably connects the rotation-side optical fiber FB1 to the fixed-side optical fiber FB2 and transmits the measurement light L1 and the return light L3 are provided.

  In the OCT processor 400 and the OCT probe 600 shown in FIG. 2, various light including the above-described emission light La, aiming light Le, measurement light L1, reference light L2, return light L3, etc. Various optical fibers FB (FB3, FB4, FB5, FB6, FB7, FB8, etc.) including the rotation side optical fiber FB1 and the fixed side optical fiber FB2 are used as light paths for guiding and transmitting between the components. It is used.

  The first light source unit 12 emits light for OCT measurement (for example, wavelength-variable laser light in the infrared region or low-coherence light). The first light source unit 12 of this example emits a laser beam La (for example, a laser beam centered on a wavelength of 1.3 μm) while sweeping the optical frequency (wavelength) at a constant period in the infrared wavelength region. It is a variable light source.

  The first light source unit 12 includes a light source 12a that emits laser light or low-coherence light La, and a lens 12b that condenses the light La emitted from the light source 12a. Further, as will be described in detail later, the light La emitted from the first light source unit 12 is divided into the measurement light L1 and the reference light L2 by the optical fiber coupler 14 via the optical fibers FB4 and FB3, and the measurement light L1 is Input to the optical connector 18.

  The second light source unit 13 emits visible light so as to make it easy to confirm the measurement site as the aiming light Le. For example, red semiconductor laser light having a wavelength of 660 nm, He—Ne laser light having a wavelength of 630 nm, blue semiconductor laser light having a wavelength of 405 nm, or the like can be used. The second light source unit 13 in this embodiment includes, for example, a semiconductor laser 13a that emits red, blue, or green laser light, and a lens 13b that condenses the aiming light Le emitted from the semiconductor laser 13a. . The aiming light Le emitted from the second light source unit 13 is input to the optical connector 18 through the optical fiber FB8.

  In the optical connector 18, the measurement light (first light beam) L 1 and the aiming light (second light beam) Le are combined and guided to the rotation side optical fiber FB 1 in the OCT probe 600.

  The optical fiber coupler (branching / combining unit) 14 is composed of, for example, a 2 × 2 optical fiber coupler, and is optically connected to the fixed-side optical fiber FB2, the optical fiber FB3, the optical fiber FB5, and the optical fiber FB7, respectively. ing.

  The optical fiber coupler 14 divides the light La incident from the first light source unit 12 through the optical fibers FB4 and FB3 into measurement light (first light flux) L1 and reference light L2, and the measurement light L1 is fixed. The light is incident on the optical fiber FB2, and the reference light L2 is incident on the optical fiber FB5.

  Further, the optical fiber coupler 14 includes a reference light L2 which is incident on the optical fiber FB5 and is frequency-shifted and changed in optical path length by an optical path length adjusting unit 26 which will be described later and returned to the optical fiber FB5, and an OCT probe 600 which will be described later. The acquired light L3 guided from the fixed side optical fiber FB2 is multiplexed and emitted to the optical fiber FB3 (FB6) and the optical fiber FB7.

  The OCT probe 600 is connected to the fixed optical fiber FB2 via the optical connector 18, and the measurement light L1 combined with the aiming light Le is rotated from the fixed optical fiber FB2 via the optical connector 18. The light enters the side optical fiber FB1. The measurement light L1 combined with the incident aiming light Le is transmitted by the rotation side optical fiber FB1, and is irradiated to the measurement object S. Then, the return light L3 from the measuring object S is acquired, the acquired return light L3 is transmitted by the rotation side optical fiber FB1, and is emitted to the fixed side optical fiber FB2 via the optical connector 18.

  The interference light detection unit 20 is connected to the optical fibers FB6 and FB7, and uses the interference light L4 and L5 generated by combining the reference light L2 and the return light L3 by the optical fiber coupler 14 as interference signals. It is to detect.

  A detector 30a for detecting the light intensity of the interference light L4 is provided on the optical path of the optical fiber FB6 branched from the optical fiber coupler 28, and the light intensity of the interference light L5 is detected on the optical path of the optical fiber FB7. A detector 30b is provided. The interference light detection unit 20 generates an interference signal based on the detection results of the detectors 30a and 30b.

  The signal processing unit 22 acquires tomographic information from the interference signal detected by the interference light detection unit 20, and outputs a tomographic image obtained by imaging the acquired tomographic information to the monitor device 500. In the present embodiment, a corrected image in which liquid suspended matters (for example, gall mud) in the lumen are removed from the tomographic image is generated and output to the monitor device 500. The signal processing unit 22 will be described in detail later.

  The optical path length adjustment unit 26 for changing the optical path length of the reference light L2 is disposed on the emission side of the reference light L2 of the optical fiber FB5 (that is, the end of the optical fiber FB5 opposite to the optical fiber coupler 14). ing.

  The optical path length adjustment unit 26 includes a first optical lens 80 that converts the light emitted from the optical fiber FB5 into parallel light, a second optical lens 82 that condenses the light converted into parallel light by the first optical lens 80, and The reflection mirror 84 that reflects the light collected by the second optical lens 82, the base 86 that supports the second optical lens 82 and the reflection mirror 84, and the base 86 are moved in a direction parallel to the optical axis direction. And a mirror moving mechanism 88. By changing the distance between the first optical lens 80 and the second optical lens 82, the optical path length of the reference light L2 is adjusted.

  The first optical lens 80 converts the reference light L2 emitted from the core of the optical fiber FB5 into parallel light, and condenses the reference light L2 reflected by the reflection mirror 84 on the core of the optical fiber FB5.

  The second optical lens 82 condenses the reference light L2 converted into parallel light by the first optical lens 80 on the reflection mirror 84 and makes the reference light L2 reflected by the reflection mirror 84 parallel light. Thus, the first optical lens 80 and the second optical lens 82 form a confocal optical system.

  Further, the reflection mirror 84 is disposed at the focal point of the light collected by the second optical lens 82 and reflects the reference light L2 collected by the second optical lens 82.

  As a result, the reference light L2 emitted from the optical fiber FB5 becomes parallel light by the first optical lens 80 and is condensed on the reflection mirror 84 by the second optical lens 82. Thereafter, the reference light L2 reflected by the reflection mirror 84 becomes parallel light by the second optical lens 82 and is condensed by the first optical lens 80 on the core of the optical fiber FB5.

  The base 86 fixes the second optical lens 82 and the reflecting mirror 84, and the mirror moving mechanism 88 moves the base 86 in the optical axis direction of the first optical lens 80 (the direction of arrow A in FIG. 2). .

  By moving the base 86 in the direction of arrow A with the mirror moving mechanism 88, the distance between the first optical lens 80 and the second optical lens 82 can be changed, and the optical path length of the reference light L2 can be adjusted. Can do.

  The operation control unit 32 includes input means such as a keyboard and a mouse, and control means for managing various conditions based on input information, and is connected to the signal processing unit 22. The operation control unit 32 inputs, sets, and changes various processing conditions and the like in the signal processing unit 22 based on an operator instruction input from the input unit.

  Note that the operation control unit 32 may display the operation screen on the monitor device 500, or may provide a separate display unit to display the operation screen. Further, the operation control unit 32 controls the operation of the first light source unit 12, the second light source unit 13, the optical connector 18, the interference light detection unit 20, the optical path length, the detectors 30a and 30b, and sets various conditions. You may do it.

  FIG. 3 is a cross-sectional view of the OCT probe 600. As shown in FIG. 3, the distal end portion of the insertion portion 602 includes a probe outer tube (sheath) 620, a cap 622, a rotation side optical fiber FB1, a spring 624, a fixing member 626, and an optical lens 628. doing.

  The probe outer cylinder 620 is a cylindrical member having flexibility, and is made of a material through which the measurement light L1 combined with the aiming light Le and the return light L3 are transmitted in the optical connector 18. The probe outer cylinder 620 is a tip through which the measurement light L1 (aiming light Le) and the return light L3 pass (the tip of the rotation side optical fiber FB1 opposite to the optical connector 18, hereinafter referred to as the tip of the probe outer cylinder 620). It is only necessary that a part of the side is made of a material that transmits light over the entire circumference (transparent material), and parts other than the tip may be made of a material that does not transmit light.

  The cap 622 is provided at the distal end of the probe outer cylinder 620 and closes the distal end of the probe outer cylinder 620.

  The cap 622 is formed with a guide wire hole 623 for inserting a guide wire. The guide wire hole 623 has one opening 623A on the side surface of the cap 622 and the other opening on the front surface. 623B. The guide wire is arranged in advance at the measurement site and guides the OCT probe 600 to the position. The guide wire arranged at the measurement position is inserted into the guide wire hole 623, and the OCT probe 600 is moved forward. , The OCT probe 600 can be guided to the guide wire and moved to the measurement site. By guiding the OCT probe 600 using the guide wire in this way, the OCT probe 600 can be easily placed in the bile duct or pancreatic duct where it is difficult to directly enter the OCT probe 600.

  The rotation-side optical fiber FB1 is a linear member and is accommodated in the probe outer cylinder 620 along the probe outer cylinder 620. The rotation-side optical fiber FB1 guides the measurement light L1 combined with the optical connector 18 and the aiming light Le to the optical lens 628 and irradiates the measurement target S with the measurement light L1 (aiming light Le). The return light L3 from the measuring object S acquired by the lens 628 is guided to the optical connector 18. The return light L3 enters the fixed side optical fiber FB2 via the optical connector 18. The rotation-side optical fiber FB1 is disposed so as to be rotatable with respect to the probe outer cylinder 620 and movable in the axial direction of the probe outer cylinder 620.

  The spring 624 is fixed to the outer periphery of the rotation side optical fiber FB1. The rotation-side optical fiber FB1 and the spring 624 are connected to the optical connector 18 together with the rotating cylinder 656.

  The optical lens 628 is disposed at the measurement-side tip of the rotation-side optical fiber FB1 (tip of the rotation-side optical fiber FB1 opposite to the optical connector 18). The distal end portion (light emission surface) of the optical lens 628 is formed in a substantially spherical shape for condensing the measurement light L1 (aiming light Le) emitted from the rotation-side optical fiber FB1 onto the measurement target S. .

  The optical lens 628 irradiates the measurement target S with the measurement light L1 (aiming light Le) emitted from the rotation side optical fiber FB1, collects the return light L3 from the measurement target S, and enters the rotation side optical fiber FB1. .

  The fixing member 626 is disposed on the outer periphery of the connection portion between the rotation side optical fiber FB1 and the optical lens 628, and fixes the optical lens 628 to the end portion of the rotation side optical fiber FB1. The fixing method of the rotation side optical fiber FB1 and the optical lens 628 by the fixing member 626 is not particularly limited, and the fixing member 626, the rotation side optical fiber FB1, and the optical lens 628 may be bonded and fixed by an adhesive. It may be fixed with a mechanical structure using bolts or the like. Any fixing member 626 may be used as long as it is used for fixing, holding or protecting the optical fiber, such as a zirconia ferrule or a metal ferrule.

  The rotation-side optical fiber FB1 and the spring 624 are connected to the rotation cylinder 656. By rotating the rotation-side optical fiber FB1 and the spring 624 by the rotation cylinder 656, the optical lens 628 is moved with respect to the probe outer cylinder 620 by an arrow R2. Rotate in the direction (rotation direction with the optical axis of the rotation side optical fiber FB1 as the rotation center). The optical connector 18 includes a rotary encoder. Based on the signal from the rotary encoder, the irradiation position of the measuring light L1 is detected from the position information (angle information) of the optical lens 628. That is, the measurement position is detected by detecting the angle of the rotating optical lens 628 with respect to the reference position in the rotation direction.

  Further, the rotation-side optical fiber FB1, the spring 624, the fixing member 626, and the optical lens 628 are moved inside the probe outer cylinder 620 in the directions indicated by arrows S1 (forceps opening direction) and S2 (outside the probe) by a drive mechanism including a motor 660. It is configured to be movable in the direction of the tip of the cylinder 620.

  On the left side of FIG. 3, a schematic configuration of a drive mechanism such as the rotation-side optical fiber FB1 in the operation unit 604 of the OCT probe 600 is shown.

  The probe outer cylinder 620 is fixed to the fixing member 670, while the rotation-side optical fiber FB 1 and the base end portion of the spring 624 are connected to the rotation cylinder 656. The rotating cylinder 656 is configured to rotate via a gear 654 in accordance with the rotation of the motor 652. The rotary cylinder 656 is connected to the optical connector 18, and the measurement light L1 and the return light L3 are transmitted between the rotation side optical fiber FB1 and the fixed side optical fiber FB2 via the optical connector 18.

  The frame 650 including the rotary cylinder 656, the motor 652, the gear 654, and the optical connector 18 includes a support member 662. The support member 662 has a screw hole (not shown), and a ball screw 664 for advancing / retreating is engaged with the screw hole. A motor 660 is connected to the ball screw 664 for advancing / retreating movement. By rotating and driving the motor 660, the frame 650 is moved back and forth, whereby the rotation-side optical fiber FB1, the spring 624, the fixing member 626, and the optical lens 628 are moved in the S1 and S2 directions in FIG. , That is, the direction along the optical axis of the rotation-side optical fiber FB1).

  The OCT probe 600 is configured as described above, and the measurement light emitted from the optical lens 628 when the rotation-side optical fiber FB1 and the spring 624 are rotated in the direction of the arrow R2 in FIG. L1 (aiming light Le) is irradiated onto the measuring object S while scanning in the direction of arrow R2 (circumferential direction of the probe outer cylinder 620), and the return light L3 is acquired. The aiming light Le is applied to the measuring object S as, for example, blue, red, or green spot light. The reflected light of the aiming light Le (reflected light from the measuring object S) is also displayed as a bright spot on the observation image displayed on the monitor device 500.

  By such optical scanning along the rotation direction, a desired part of the measuring object S can be accurately captured on the entire circumference of the probe outer cylinder 620 in the circumferential direction, and the return light L3 reflected from the measuring object S is obtained. Can be acquired.

  Furthermore, when acquiring tomographic information of a three-dimensional area for generating three-dimensional volume data, the end of the movable range of the rotation side optical fiber FB1 and the optical lens 628 in the direction of the arrow S1 is driven by a drive mechanism including a motor 66. And move to the end of the movable range while alternately acquiring the tomographic information and moving the predetermined amount in the S2 direction while acquiring the tomographic information.

  In this way, three-dimensional volume data can be obtained by acquiring tomographic information in a desired range for the measurement target S.

  FIG. 4 is a diagram showing a scan surface of tomographic information when the optical scanning is radial scan with respect to the measurement target S, and FIG. 5 is a diagram showing three-dimensional volume data constructed by the tomographic information of FIG. . By acquiring tomographic information in the depth direction (Z direction) of the measurement target S from the interference signal, the measurement target S is scanned (radial scan) in the direction of arrow R2 (circumferential direction of the probe outer cylinder 620) in FIG. As shown in FIG. 4, tomographic information on the scan plane composed of the Z direction and the X direction orthogonal to the Z direction can be acquired. Furthermore, by moving the scan plane along the Y direction orthogonal to the scan plane, as shown in FIG. 5, tomographic information of a three-dimensional area for generating three-dimensional volume data can be acquired.

  FIG. 6 is a diagram illustrating a state in which tomographic information is obtained using the OCT probe 600 derived from the forceps port 156 of the endoscope 100. As shown in FIG. 6, tomographic information is obtained by bringing the distal end portion of the insertion portion 602 of the OCT probe 600 close to a desired portion of the measurement target S. When acquiring tomographic information of a desired three-dimensional region, it is not always necessary to move the OCT probe 600 main body, and the optical lens 628 may be moved within the probe outer cylinder 620 by the drive mechanism described above.

  The diagnostic imaging apparatus 10 of the present embodiment is characterized by a tomographic image correction process performed in the signal processing unit 22 of the OCT processor 400. Hereinafter, the configuration of the signal processing unit 22 will be described.

  FIG. 7 is a block diagram showing a configuration of the signal processing unit 22 of FIG. As shown in FIG. 7, the signal processing unit 22 mainly includes a Fourier transform unit 410, a logarithmic transform unit 420, a tomographic image construction unit 450, a tomographic image correction unit 460, a memory unit 470, and a control unit 490. The

  The control unit 490 is for controlling the operation of each unit of the signal processing unit 22. In addition, a control signal is output to each unit so that various processes are performed according to the operation of the operation control unit 32.

  The memory unit 470 is for storing programs and various information necessary for the operation of each unit of the signal processing unit 22. In the present embodiment, information for detecting a probe region, a guide wire region, and a luminal tissue region from a tomographic image in a tomographic image correction unit 460 described later is stored in the memory unit 470.

  The interference signal output from the interference light detection unit 20 is input to the Fourier transform unit 410. The Fourier transform unit 410 has a function of performing frequency analysis by FFT (Fast Fourier Transform) on the input interference signal. In the Fourier transform unit 410, the intensity of the reflected light (returned light) L3 at each depth position of the measuring object S, that is, the reflection intensity data in the depth direction is generated and output by frequency analysis using FFT.

  The logarithmic transformation unit 420 receives the reflection intensity data output from the Fourier transformation unit 410. The logarithmic conversion unit 420 has a function of performing logarithmic conversion in order to widen the dynamic range of the reflection intensity data. The logarithmic conversion unit 420 outputs logarithmically converted reflection intensity data.

  The tomographic image construction unit 450 receives the reflection intensity data output from the logarithmic conversion unit 420. The tomographic image construction unit 450 has an image processing function for visualizing the reflection intensity data as a tomographic image. For example, the tomographic image construction unit 450 is adapted to a scanning method such as brightness, contrast adjustment, resampling according to the display size, and radial scanning. Perform coordinate transformation of. The tomographic image construction unit 450 generates tomographic image data indicating a tomographic image, and the tomographic image data is output to the tomographic image correction unit 460 or the monitor device 500.

  The tomographic image data output from the tomographic image construction unit 450 is input to the tomographic image correction unit 460. The tomographic image correction unit 460 has a correction function for removing (non-displaying) a predetermined object from the tomographic image based on the tomographic image data. Although the correction process performed by the tomographic image correction unit 460 will be described in detail later, an object having an indefinite shape such as a liquid suspended matter (for example, gall mud) in the lumen is detected and non-corrected. A feature is that a corrected tomographic image that is displayed is generated. The tomographic image correction unit 460 outputs corrected tomographic image data that has been subjected to correction processing.

  Next, the operation of the present embodiment configured as described above will be described.

  First, when the OCT probe 600 is inserted into a lumen such as a bile duct or pancreatic duct, a guide wire is placed in the lumen in advance. Since the method of placing the guide wire is well known, the description is omitted here. Then, the guide wire is passed through the guide wire hole 623 of the OCT probe 600 shown in FIG. 3 from the proximal end side, the OCT probe 600 is inserted into the lumen along the guide wire, and is arranged at the site to be measured.

  Next, the measurement light L1 (aiming light Le) is emitted from the optical lens 628 disposed at the distal end of the OCT probe 600 to the measurement target in a state where the distal end of the OCT probe 600 is in close contact with the inner wall surface in the lumen. The measurement is performed. Here, as an example, FIG. 8 is a schematic diagram (a cross-sectional view in a direction perpendicular to the axial direction of the OCT probe 600) schematically showing a state where measurement is performed by the OCT probe 600 inserted into the bile duct. Show. In FIG. 8, reference numeral 700 represents a guide wire, and reference numeral 704 represents gall mud. In FIG. 8, illustrations of built-in components (such as the optical lens 628 and the optical fiber FB1) of the OCT probe 600 are omitted.

  When the measurement by the OCT probe 600 is started, the interference light detection unit 20 shown in FIG. 7 receives reflected light L3 and reference light L2 obtained when the measurement light L1 is irradiated from the OCT probe 600 to the measurement object S. The interference light when the two are combined is input to the interference light detection unit 20. Note that the reference light L2 is obtained by dividing the light emitted from the first light source unit 12 as described above.

  As shown in FIG. 7, in the interference light detection unit 20, the interference signal generation unit 20a performs processing to convert the interference light (optical signal) into an interference signal (electric signal), and the AD conversion unit 20b converts the interference signal. A process of converting an analog signal into a digital signal is performed. In the AD converter 20b, for example, conversion from an analog signal to a digital signal is performed with a sampling rate of about 80 MHz and a resolution of about 14 bits. However, the value is not particularly limited to these values. The interference signal converted into a digital signal by the AD conversion unit 20 b is output to the signal processing unit 22.

  The interference signal input to the signal processing unit 22 is subjected to frequency analysis by FFT (Fast Fourier Transform) in the Fourier transform unit 410. Thereby, the intensity | strength of the reflected light (return light) L3 in each depth position of the measuring object S, ie, the reflection intensity data of a depth direction, is produced | generated. The reflection intensity data is logarithmically converted by the logarithmic conversion unit 420 and output to the tomographic image construction unit 450.

  The tomographic image construction unit 450 performs image processing such as coordinate conversion according to a scanning method such as brightness, contrast adjustment, resample according to the display size, radial scanning, etc., on the input reflection intensity data. Tomographic image data is generated as data indicating an image. The tomographic image data is output to the tomographic image correction unit 460 or the monitor device 500.

  The tomographic image correction unit 460 performs correction processing for removing (non-displaying) a predetermined object from the tomographic image based on the tomographic image data. The corrected image data indicating the corrected tomographic image is output to the monitor device 500.

  As a result, a tomographic image based on the tomographic image data or a corrected tomographic image based on the corrected image data is displayed on the monitor device 500, enabling diagnosis. The image displayed on the monitor device 500 can be selected by the operator from the input means of the operation control unit 32.

  Here, tomographic image correction processing performed in the signal processing unit 22 will be described. FIG. 9 is a flowchart showing the flow of processing performed by the tomographic image correction unit 460 of FIG. Hereinafter, each process shown in FIG. 8 will be described in detail.

  First, tomographic image data is acquired from the tomographic image construction unit 450 (step S10). An example of the tomographic image generated from the tomographic image data acquired at this time is shown in FIG. The tomographic image shown in FIG. 10 is shown in a two-dimensional polar coordinate system, the horizontal axis indicates the circumferential position (rotation angle) θ around the long axis of the OCT probe 600, and the vertical axis indicates the OCT probe 600. The depth position r in the emission direction of the measurement light L1 emitted from the light emission end (the direction of the optical axis of the measurement light L1 and the depth direction of the measurement object S) is shown, and the vertical axis downward is This is the emission direction of the measurement light L1.

  The tomographic image shown in FIG. 10 is acquired using the OCT probe 600 inserted into the bile duct. This tomographic image includes a probe outer cylinder 620 of the OCT probe 600 and a guide wire 700 used as an insertion assisting tool when the OCT probe 600 is inserted into the bile duct. Further, gallbladder mud 704 is included as a liquid suspended matter floating in a lumen tissue 702 corresponding to the inner wall portion of the bile duct and an internal region (liquid region) in the bile duct.

  Next, a probe region is detected from the tomographic image (step S12). Information relating to the shape, size, position, contrast, etc. of the OCT probe 600 is stored in the memory unit 470 of the signal processing unit 22 as information for detecting the OCT probe 600 (OCT information). The tomographic image correction unit 460 detects a probe region from the tomographic image based on the OCT information.

  Here, a method using dynamic programming will be described as an example of a probe region detection method. In this method, first, an edge enhancement filter (for example, a 2D Gabor filter or the like) is applied to a tomographic image generated from the tomographic image data acquired in step S10, for example, the tomographic image (original image) shown in FIG. Then, an edge-enhanced image in which a line indicating the inner wall surface of the probe outer cylinder 620 of the OCT probe 600 is emphasized is generated.

  Next, the sign of the edge-enhanced image generated as described above is inverted, and the edge to be detected is converted into a cost image having a negative value. Then, in the search range (for example, r = 3 to 60 pixels) on the cost image, a path having a minimum integrated cost value from the left end to the right end of the image is detected by dynamic programming. At this time, the range in the vertical direction (r direction) for searching for the local accumulated cost minimum value by dynamic programming is limited to the current pixel of interest ± 1, and the shape of the search path is stepwise in the vertical direction. Adjustments are made so that there is no significant shift. As a result, as shown in FIG. 11, a path (minimum cost path) 706 having the smallest accumulated cost value detected last becomes a line indicating the inner wall surface of the probe outer cylinder 620.

  Next, the minimum cost path 706 (that is, a line indicating the inner wall surface of the probe outer cylinder 620) obtained as described above is shifted downward (r direction) by the thickness of the side wall portion of the probe outer cylinder 620. As shown in FIG. 12, the probe surface line 708 is detected as a line indicating the outer wall surface of the probe outer cylinder 620. In this example, the minimum cost path 706 is shifted downward by 30 pixels. Then, the region above the probe surface line 708 (the direction from the outer periphery of the OCT probe 600 toward the central axis) is detected as a probe region.

  This completes the description of the method using dynamic programming. Note that the probe region detection method is not limited to a method using dynamic programming, and other methods may be used.

  Next, a guide wire region is detected from the tomographic image (step S14). Information relating to the shape, size, position, contrast, etc. of the guide wire 700 is stored in the memory unit 470 of the signal processing unit 22 as information for detecting the guide wire 700 (guide wire information). The tomographic image correction unit 460 detects a guide wire region from the tomographic image based on the guide wire information.

  Here, a method using an edge enhancement filter will be described as an example of a method for detecting a guide wire region. In this method, first, a multi-directional edge enhancement filter (for example, a 2D Gabor filter) is applied to the tomographic image generated from the tomographic image data acquired in step S10, for example, the image shown in FIG. Then, the results obtained by applying these edge enhancement filters are integrated to generate an integrated filter image. The integrated filter image is binarized with a strict threshold α (for example, α = −90.0) with respect to the negative filter value, and a region having the maximum area is extracted from the extracted regions. At this time, as shown in FIG. 13, if the area of the extraction region is within a predetermined range (for example, an area corresponding to 100 to 2500 pixels), the region is detected as a guide wire 700.

  The above is the description of the method using the edge enhancement filter. Note that the guide wire region detection method is not limited to the method using the edge enhancement filter, and other methods may be used.

  Next, a luminal tissue region is detected from the tomographic image (step S16). The memory unit 470 of the signal processing unit 22 stores information on the shape, size, position, contrast, and the like of the luminal tissue to be diagnosed as information (luminal tissue information) for detecting the luminal tissue. ing. The tomographic image correction unit 460 detects the luminal tissue region from the tomographic image based on the luminal tissue information.

  Here, a method using a region extraction method will be described as an example of a method for detecting a luminal tissue region. In this method, first, a Gaussian smoothing filter with σ = 2.0 (pixels) is applied to a tomographic image generated from the tomographic image acquired in step S10, for example, the tomographic image (original image) shown in FIG. To generate an image from which high-frequency noise has been removed.

  Next, an image obtained by modeling the background component due to the attenuation of the measurement light L1 emitted from the optical lens 628 of the OCT probe 600 as an exponential function with respect to the original image (that is, the tomographic image shown in FIG. 10). A background component image is generated by least square fitting. In this example, the following model formula is used.

Here, although the left side is P (r, θ), θ is an isotropic OCT light emission angle, and the right side of the above expression does not include θ dependency. However, as fitting data, pixel values at all θ are used. In order to reduce the least squares method to a simple linear problem, an average value c ₀ of pixel values in the lower 20 pixel region in the vertical (r) direction is obtained in advance and substituted for the constant term c.

  Finally, the background component image P (r, θ) is subtracted from the image from which the high frequency noise has been removed to generate a differential image from which the high frequency noise and the background component have been removed from the original image.

  Next, a candidate region on the surface of the luminal tissue is obtained from the difference image by hysteresis binarization. At this time, the threshold value for hysteresis binarization uses a higher threshold value H and a lower threshold value L. In this example, H = 45.0 and L = 15.0. In the hysteresis binarization process, as shown in FIG. 14, a detection region based on a higher threshold value H and a lower threshold value L is obtained. Then, among the regions detected by the lower threshold L, only the region including the region detected by the higher threshold H is left, and a final binarization result as shown in FIG. 15 is obtained.

  Next, for each binarized region (each region shown in white in FIG. 15), feature quantities such as area, circularity, and contrast are calculated. Threshold processing is performed on these feature amounts, and binarized areas determined as noise areas (FP areas) are deleted.

  Next, a circle with a certain radius (for example, 15 pixels) is drawn around each pixel of each binarized area, and an area where adjacent circles overlap is regarded as one cluster. Among each cluster, a cluster having the largest area is detected as a luminal tissue region. In the example shown in FIG. 15, a region having the maximum area is detected as the luminal tissue 702.

  The above is the description of the method using the region extraction method. The method for detecting the luminal tissue region is not limited to the method using the region extraction method, and other methods may be used.

  Next, a liquid suspended matter region is detected from the tomographic image (step S18). In the present embodiment, as a method for detecting a liquid suspended matter region, each region (that is, a probe region, a guide wire region, and a lumen tissue region) detected in steps S12 to S16 from the tomographic image shown in FIG. ) Is subtracted. As a result, for example, as shown in FIG. 16, gall mud 704 is detected from the tomographic image as a liquid suspended matter region. According to this method, the liquid suspended substance in the lumen, that is, an object having an indefinite shape can be easily detected by a simple method without performing complicated processing.

  Next, a corrected tomographic image in which the probe region, the guide wire region, and the liquid suspended matter region are removed from the tomographic image is generated (step S20). Thereby, a corrected tomographic image as shown in FIG. 17 is obtained. At this time, it is preferable that the pixels in each region to be removed are subjected to interpolation processing with the same or similar color as the surrounding pixels in each region.

  Finally, the corrected image data is output to the monitor device 500 as data for generating a corrected tomographic image (step S22). Accordingly, a corrected tomographic image from which the OCT probe 600, the guide wire 700, and the gall mud 704 are removed is displayed on the monitor device 500.

  In this embodiment, a corrected tomographic image in which the probe region, the guide wire region, and the liquid suspended region are removed from the tomographic image is automatically generated. You may enable it to select individually the area | region to display or hide. This selection may be performed by an operator from the input means of the operation control unit 32. The control unit 490 changes the setting of the correction processing condition of the tomographic image correction unit 460 according to the information selected by the operation control unit 32. As a result, a corrected tomographic image according to the operator's intention can be output, and convenience is improved.

  In FIG. 8, the order in which the processes shown in steps S12, S14, and S16 are performed is not limited. For example, the order may be reverse to the example shown in FIG. 8, and the processes are performed in parallel. May be.

  As described above, according to the diagnostic imaging apparatus 10 of the present embodiment, the probe region, the guide wire region, and the luminal tissue region are detected from the tomographic image acquired by the OCT measurement, and these regions are subtracted from the tomographic image. Thus, it is possible to detect the area of the liquid suspended matter in the lumen. Accordingly, it is possible to easily provide a corrected image in which the liquid suspended matter in the lumen is removed from the tomographic image. As a result, it is possible to display a corrected image in which information not directly related to diagnosis is removed from a tomographic image, and the efficiency and accuracy of diagnosis can be improved.

  In the present embodiment, the case where a tomographic image in the bile duct is acquired has been described as an example. However, the present invention is not limited to this, and a region in which a lumen is filled with liquid and a suspended matter (liquid suspended matter) exists therein For example, it can be applied to pancreatic ducts, blood vessels, ureters, and the like.

  In the above-described embodiment, the SS-OCT (Swept Source OCT) apparatus has been described as the OCT processor 400. However, the present invention is not limited to this, and the OCT processor 400 can also be applied as an SD-OCT (Spectral Domain OCT) apparatus. It is.

As described above, the optical tomographic image processing apparatus and the operation method of the optical tomographic image processing apparatus of the present invention have been described in detail. Of course, improvements and modifications may be made.

  DESCRIPTION OF SYMBOLS 10 ... Diagnostic imaging apparatus, 20 ... Interference light detection part, 20a ... Interference signal generation part, 20b ... AD conversion part, 22 ... Signal processing part, 100 ... Endoscope, 200 ... Endoscope processor, 300 ... Light source device, 400 ... OCT processor, 410 ... Fourier transform unit, 420 ... logarithmic transformation unit, 450 ... tomographic image construction unit, 460 ... tomographic image correction unit, 490 ... control unit, 500 ... monitor device

Claims (14)

Image acquisition means for acquiring an optical tomographic image in the lumen by optical coherence tomography measurement;
A lumen insert detection means for detecting a region of a lumen insert inserted into the lumen from the optical tomographic image;
A lumen tissue detecting means for detecting a tissue region of the lumen from the optical tomographic image;
Liquid for detecting a region of liquid suspended matter floating in the liquid in the lumen from the optical tomographic image by subtracting the region of the luminal insert and the tissue region of the lumen from the optical tomographic image Suspended matter detection means;
Correction image generation means for generating a correction image in which the liquid suspension is removed from the optical tomographic image based on the detection result of the liquid suspension detection means;
An optical tomographic image processing apparatus comprising:   The optical tomographic image processing apparatus according to claim 1, wherein the luminal insert detection unit detects a region of the optical probe inserted into the lumen as a region of the luminal insert.   The optical tomography according to claim 2, wherein the lumen insert detection means detects a region of a guide wire for guiding the optical probe into the lumen as a region of the lumen insert. Image processing device.   The correction image generation unit generates a correction image in which the lumen insertion and the liquid suspension are removed from the optical tomographic image based on detection results of the lumen insertion detection unit and the liquid suspension detection unit. The optical tomographic image processing apparatus according to claim 1, wherein: Instructing means for selectively instructing whether or not to remove each region detected by the luminal insert detection means and the liquid suspended matter detection means from the optical tomographic image,
The correction image generation unit generates a correction image in which the luminal insert and the liquid suspended matter are selectively removed from the optical tomographic image in accordance with an instruction from the instruction unit. Optical tomographic image processing device.   The optical tomographic image processing apparatus according to claim 1, further comprising display means for displaying the correction image generated by the correction image generation means.   The optical tomographic image processing apparatus according to claim 1, wherein the lumen is a bile duct, a pancreatic duct, a blood vessel, or a ureter. An operation method of an optical tomographic image processing apparatus,
An image acquisition step in which the image acquisition means acquires an optical tomographic image in the lumen by optical coherence tomography measurement;
A luminal insert detection means for detecting a region of the luminal insert inserted into the lumen from the optical tomographic image; and
Luminal tissue detection means, a lumen tissue detection step of detecting a tissue region of the lumen from the optical tomographic image,
The liquid floating substance detection means subtracts the region of the luminal insert and the tissue region of the lumen from the optical tomographic image, thereby floating the liquid floating in the liquid in the lumen from the optical tomographic image. A liquid suspended matter detection process for detecting an area of an object,
A corrected image generating unit that generates a corrected image in which the liquid suspended matter is removed from the optical tomographic image based on the detection result of the liquid suspended matter detecting step;
A method of operating an optical tomographic image processing apparatus, comprising : 9. The luminal insert detection step, wherein the luminal insert detection means detects a region of an optical probe inserted into the lumen as a region of the luminal insert. A method of operating the described optical tomographic image processing apparatus . The lumen insert detection step is characterized in that the lumen insert detection means detects a region of a guide wire for guiding the optical probe into the lumen as a region of the lumen insert. An operating method of the optical tomographic image processing apparatus according to claim 9. In the correction image generation step, the correction image generation means determines that the lumen insert and the liquid suspension are generated from the optical tomographic image based on the detection results of the lumen insertion detection step and the liquid suspension detection step. The operation method of the optical tomographic image processing apparatus according to any one of claims 8 to 10, wherein the corrected image removed is generated. The instruction means includes an instruction step for selectively instructing whether to remove each region detected by the lumen insertion detection step and the liquid suspended matter detection step from the optical tomographic image,
The correction image generation step generates a correction image in which the luminal insert and the liquid suspended matter are selectively removed from the optical tomographic image in accordance with an instruction of the instruction step. Method of the optical tomographic image processing apparatus . The operation method of the optical tomographic image processing apparatus according to claim 8 , wherein the display unit includes a display step of displaying the correction image generated by the correction image generation step. The method of operating an optical tomographic image processing apparatus according to any one of claims 8 to 13, wherein the lumen is a bile duct, a pancreatic duct, a blood vessel, or a ureter.