JP2017064220A - Optical coherence tomography apparatus - Google Patents

Abstract

PROBLEM TO BE SOLVED: To provide an optical coherence tomography apparatus that easily obtains excellent three-dimensional OCT data.SOLUTION: The optical coherence tomography apparatus splits light output from a light source into measurement light and reference light, illuminates a subject with the measurement light through a probe inserted into the subject and scans the measurement light repeatedly, and detects interference between the reflected measurement light and the reference light. The optical coherence tomography apparatus allows a control unit to form two-dimensional OCT data along plural scan lines based on signals from a detector as at least a portion of the probe is moved relative to the subject, and to then arrange plural sets of two-dimensional OCT data to obtain three-dimensional OCT data of the subject. The control unit receives a selection instruction from an operator as to the condition of prove movement for obtaining plural two-dimensional OCT data sets to be used as a base of three-dimensional OCT data, so as to adjust the relative positional relationship between the plural two-dimensional OCT data sets in the three-dimensional OCT data, based on the movement condition.SELECTED DRAWING: Figure 9

Description

  The present disclosure relates to an optical tomography apparatus that captures tomographic images of a tissue of a subject.

  2. Description of the Related Art Conventionally, an apparatus using an optical coherence tomography (OCT) is known as an apparatus that can take a tomographic image at a predetermined part of a subject. An optical tomography apparatus using OCT divides light emitted from a light source into measurement light and reference light, and irradiates the divided measurement light while scanning the tissue of the subject. The measurement light reflected by the tissue is combined with the reference light, and information on the depth direction of the tissue is acquired from the interference signal of the combined light. The optical tomography apparatus can generate two-dimensional OCT data using the acquired information in the depth direction. In addition, by arranging a plurality of two-dimensional OCT data with slightly different scanning lines, three-dimensional OCT data of the subject can be constructed (see Patent Document 1).

  An optical tomographic imaging apparatus that captures a tomographic image of a tissue from within the subject by irradiating measurement light from the tip of a probe that can be inserted into the subject is known (see Patent Document 2). As this type of apparatus, an apparatus that scans measurement light on a subject by driving an optical member provided inside a probe has been proposed.

JP 2010-110393 A JP 2014-188276 A

  Here, in the probe-type apparatus, two-dimensional OCT data is acquired at different scanning lines by moving at least a part of the probe relative to the subject. However, in the conventional apparatus, when three-dimensional OCT data is formed from a plurality of two-dimensional OCT data obtained in this way, a condition for adjusting the positional relationship of each two-dimensional OCT data in the three-dimensional OCT data is set. The operator (for example, the operator of the probe or its assistant) could not be selected from a plurality of conditions. For this reason, the case where 3D OCT data cannot be formed appropriately is considered.

  The present disclosure has been made in view of the problems of the prior art, and an object thereof is to provide an optical tomography apparatus that can easily acquire good three-dimensional OCT data.

 The optical tomography apparatus according to the first aspect of the present disclosure divides light output from a light source into measurement light and reference light, and passes the measurement light onto the subject via a probe inserted into the subject. And an optical tomography apparatus for detecting interference between the reflected light of the measurement light and the reference light by a detector, wherein at least the probe is applied to the subject. As the part is moved, two-dimensional OCT data of the subject in a plurality of scanning lines is formed based on a signal from the detector, and further, the plurality of two-dimensional OCT data are arranged side by side. Image forming means for acquiring three-dimensional OCT data, and an instruction for accepting a selection instruction from an operator regarding the probe movement condition when acquiring a plurality of two-dimensional OCT data as a basis of the three-dimensional OCT data It includes a biasing means, wherein the image forming means, the relative positional relationship between the two-dimensional OCT data in the three-dimensional OCT data is adjusted on the basis of the moving condition.

  According to the apparatus of the present disclosure, there is an effect that it is easy to acquire good three-dimensional OCT data.

It is a figure which shows schematic structure of an optical tomography apparatus and peripheral equipment. It is an enlarged view near the front-end | tip part of a probe. It is an example of the tomographic image (two-dimensional OCT data) image | photographed with the optical tomography apparatus. It is a figure explaining the method of forming a three-dimensional graphic (an example of three-dimensional OCT data) from a some tomographic image. It is an example of the three-dimensional graphic expressed by polar coordinates. It is an example of the three-dimensional graphic expressed by a rectangular coordinate. It is an example of the image which removed the reflective image by a probe from the three-dimensional graphic expressed with a polar coordinate. It is an example of the image which removed the reflective image by a probe from the three-dimensional graphic expressed with a rectangular coordinate. It is the figure which showed typically the adjustment process of the arrangement | positioning space | interval of each tomographic image contained in a three-dimensional image, (a) has shown the state before adjustment, (b) has each shown the state after adjustment. It is the figure which showed typically the adjustment process which adjusts the positional relationship of the left-right direction of each tomographic image contained in a three-dimensional image according to the inclination of a moving direction of a probe and a scanning line, (a) is adjustment The previous state, (b) shows the state after adjustment. It is the schematic diagram which showed the front image image | photographed simultaneously with the tomographic image.

  Hereinafter, one embodiment of the present disclosure will be described with reference to the drawings.

<1. Explanation of device configuration>
First, a schematic configuration of an optical tomography apparatus (hereinafter abbreviated as “imaging apparatus”) 1 according to the present embodiment will be described with reference to FIG. The imaging apparatus 1 images two-dimensional OCT data (for example, a tomographic image (B scan image)) of a tissue in a subject using a probe 2 inserted into the subject. In addition, a plurality of two-dimensional OCT data are arranged in time series to form three-dimensional OCT data of the subject. The three-dimensional OCT data may be data (for example, three-dimensional volume data and three-dimensional graphics) generated as a result of arranging a plurality of two-dimensional OCT data. Further, as the three-dimensional OCT data, a retinal surface OCT image obtained by processing the data, a C scan image showing a signal intensity distribution at a certain depth position, a layer thickness map (for example, a thickness map image) It may be a blood vessel map or the like.

  Hereinafter, as a specific example, the imaging device 1 is assumed to be an ophthalmic imaging device. That is, a tomographic image of the internal tissue (for example, retina) of the eye E is imaged by the imaging device 1. However, the present disclosure can also be applied to an apparatus that captures tomographic images of subjects other than the eyes (for example, internal organs, ears, etc.). The photographing apparatus 1 includes a measurement unit 10 and a control unit 30.

  The measurement unit 10 includes an optical tomography (OCT: Optical Coherence Tomography) configuration (for example, an interference optical system). The measurement unit 10 of this embodiment includes a measurement light source 11, an aiming light source 12, a coupler 13, a coupler 14, a reference optical system 15, a mounting unit 16, a fiber rotation motor 18, a detector (light receiving element) 19, and an optical path length changing unit 20. Is provided.

  The measurement light source 11 emits light for acquiring two-dimensional OCT data (for example, a tomographic image and an angiography in a cross-sectional direction). As an example, the imaging apparatus 1 of the present embodiment includes the measurement light source 11 that can change the wavelength of the emitted laser light at high speed, so that two-dimensional OCT data can be obtained by sweep-source OCT (SS-OCT) measurement. To get. The measurement light source 11 of the present embodiment includes a laser medium, a resonator, a wavelength selection filter, and the like. As the wavelength selection filter, for example, a combination of a diffraction grating and a polygon mirror, or a filter using a Fabry-Perot etalon can be employed.

  The aiming light source 12 emits aiming light that is visible light for indicating the irradiation position of the measurement light (that is, the acquisition position of the two-dimensional OCT data).

  The coupler 13 combines the light emitted from the measurement light source 11 and the aiming light emitted from the aiming light source 12, and matches the optical axes of the two lights. The coupler 14 divides the light incident from the coupler 13 into measurement light (sample light) and reference light. The measurement light is guided to the probe 2 mounted on the mounting unit 16. The reference light is guided to the reference optical system 15. Further, the coupler 14 combines the measurement light reflected by the eye E (reflection measurement light) and the reference light generated by the reference optical system 15 to generate interference light. The coupler 14 causes the detector 19 to receive the generated interference light.

  The reference optical system 15 returns the reference light guided from the coupler 14 to the coupler 14 again. The reference optical system 15 may be a reflection optical system (Japanese Patent Laid-Open No. 2014-188276) or a transmission optical system (Japanese Patent Laid-Open No. 2010-220774).

  The detector 19 detects an interference state between the reflected measurement light and the reference light. In other words, the detector 19 detects the interference signal of the interference light generated by the coupler 14. More specifically, in the case of Fourier domain OCT, the spectral intensity of the interference light is detected by the detector 19, and a depth profile (A scan signal) in a predetermined range is obtained by Fourier transform on the spectral intensity data. Further, by collecting depth profiles for each scanning position and arranging the depth profiles, two-dimensional OCT data (for example, B-scan image see FIG. 5) is formed.

  As described above, SS-OCT is employed in the imaging apparatus 1 of the present embodiment. However, various types of OCT can be adopted for the imaging apparatus 1. For example, any of Spectral-domain OCT (SD-OCT), Time-domain OCT (TD-OCT), and the like may be employed in the imaging apparatus 1. When employing SS-OCT, it is desirable to employ a balanced detector having a plurality of light receiving elements as the detector 19. When the balance detector is used, the imaging apparatus 1 can obtain the difference between the interference signals from the plurality of light receiving elements, and reduce unnecessary noise included in the interference signals. As a result, the quality of the two-dimensional OCT data is improved.

  A rear end portion (base end portion) of the fiber 4 in the probe 2 is detachably attached to the attachment portion (for example, connector) 16. When the probe 2 is attached to the attachment unit 16, the probe 2 is connected to the measurement light guide path (for example, the fiber 4 in the measurement unit 10) divided by the coupler 14.

  A fiber rotation motor (hereinafter abbreviated as “motor”) 18 can rotate the mounting portion 16 to which the fiber 4 is mounted about the axis of the fiber 4. That is, the motor 18 rotates the fiber 4 by rotating the mounting portion 16. As a result, in this embodiment, measurement light and aiming light are scanned (details will be described later). The motor 18 is provided with a rotation detection sensor 18a. The rotation detection sensor 18a detects the rotation of the fiber 4 at the rear end for each rotation and outputs a signal to the control unit 30 for each detection (that is, for each rotation). The signal from the rotation detection sensor 18a is used to determine the generation start timing of each two-dimensional OCT data (for example, B scan image).

  Here, the probe 2 attached to the attachment part 16 will be described with reference to FIGS. 1 and 2. The probe 2 of this embodiment includes a probe main body 3 and a fiber 4. The probe body 3 includes a hand piece 5 and a needle 6.

  The fiber 4 is inserted into the probe main body 3 and guides the measurement light and aiming light guided from the coupler 14 of the measurement unit 10 to the tip of the needle 6 from the outside of the probe main body 3.

  The fiber 4 is covered with a torque coil (not shown). The torque coil is an example of a torque transmission unit, and transmits torque from the motor 18 to the fiber 4. Thereby, the fiber 4 is rotated together with the torque coil. In this embodiment, the fiber 4 and the torque coil 7 rotate freely with respect to the handpiece 5.

  The handpiece 5 is a substantially cylindrical member that is gripped by an operator (for example, an examiner, an operator, etc.). The needle 6 is provided at the tip of the handpiece 5 and has an outer diameter smaller than the outer diameter of the handpiece 5. The tip of the needle 6 is inserted into the subject (for example, the eye E). The fiber 4 is connected to the rear end of the handpiece 5 and extends to the tip of the needle 6. The probe 2 can emit each light from the tip while scanning the measurement light and aiming light guided by the fiber 4.

  Here, with reference to FIG. 2, the structure of the front-end | tip part in the probe 2 is demonstrated in detail. A light shielding member 61, an outer cylinder 66, a holding part 68, a deflecting part 71, and the like are provided at the tip of the needle 6.

  The light shielding member 61 surrounds the periphery of the fiber 4 (particularly, the periphery of the holding unit 68 and the deflecting unit 71). In the present embodiment, the shape of the light shielding member 61 is substantially cylindrical. The light blocking member 61 is formed of a material that blocks measurement light and aiming light. A notch 62 (or opening) having a predetermined width in the scanning direction (direction around the axis) of the measurement light and aiming light is provided in the vicinity of the portion where the deflection unit 71 is located in the axial direction of the light shielding member 61. Is formed. The light emitted from the deflecting unit 71 is transmitted to the outside in the region 63 inside the notch 62 (hereinafter referred to as “transmission region 63”), but the region 64 where the notch 62 is not formed (hereinafter referred to as “transmission region 63”). In the “light shielding region 64”), light is shielded by the light shielding member 61.

  In the present embodiment, the inner surface of the light shielding member 61 is roughened. That is, a large number of fine irregularities are formed on the inner surface of the light shielding member 61. In this case, in the light shielding region 64, the light irradiated on the inner surface of the light shielding member 61 is scattered. Accordingly, the reflected light reflected by the light shielding region 64 does not return to the deflecting unit 71 as compared with the case where the inner side of the light shielding member 61 hardly scatters light (for example, when the inner surface is mirror-finished). The possibility decreases. That is, when mirror processing or the like is performed, when light is reflected in a direction different from that of the deflecting unit 71, no reflected light is incident on the deflecting unit 71. When the reflected light is scattered, the reflected light easily returns to the deflecting unit 71. Therefore, the imaging apparatus 1 can perform more reliable detection using the reflected light reflected by the light shielding region 64 when detecting that the measurement light is irradiated on the light shielding region 64.

  In addition, although the shape of the transmissive area | region 63 of this embodiment is a substantially rectangular shape, it cannot be overemphasized that the magnitude | size of the transmissive area | region 63, a shape, a number, etc. can be changed. In addition, a specific method for forming the transmission region 63 and the light shielding region 64 can be changed. For example, the light-transmitting region 63 and the light-shielding region 64 may be formed by manufacturing the light-shielding member 61 by combining a material that transmits measurement light and aiming light and a material that shields light.

  The outer cylinder 66 is made of a material that transmits measurement light and aiming light, and closes the outside of the light shielding member 61. Therefore, the outer cylinder 66 allows light to pass between the inside and the outside of the transmission region 63 while preventing blood, vitreous tissue and the like from entering inside. The outer cylinder 66 may be positioned inside the light shielding member 61.

  The holding portion 68 is a substantially cylindrical member having an outer shape, and is fixed to the light shielding member 61. An insertion hole 69 through which the fiber 4 is inserted in a rotatable state is formed in the axial center portion of the holding portion 68. The holding unit 68 holds the fiber 4 in a rotatable manner in a state where the position of the axis of the fiber 4 with respect to the light shielding member 61 is fixed.

  The deflection unit 71 is provided at the tip of the fiber 4. The deflecting unit 71 deflects the light emitted from the tip of the fiber 4. The light deflected by the deflecting unit 71 is irradiated to the tissue of the subject when passing through the transmission region 63. In the present embodiment, the light deflected by the deflecting unit 71 is collected at a predetermined distance. The deflecting unit 71 may be, for example, a ball lens or a prism. The deflecting unit 71 receives reflected measurement light reflected by the tissue and makes it incident on the fiber 4. The deflecting unit 71 of this embodiment deflects light at an angle of about 70 degrees with respect to the axial direction of the fiber 4, but the angle of deflection can be changed as appropriate. Note that a shaft 73 for suppressing twisting of the fiber 4 and the like is provided on the outer periphery of a portion of the fiber 4 on the rear end side of the holding portion 68.

  Note that the imaging apparatus 1 may include various configurations such as an optical system for adjusting the focus of the measurement light in the measurement unit 10 or the probe 2. These detailed explanations are omitted.

  Next, the control system of the apparatus will be described with reference to FIG. The control unit 30 includes a CPU (processor) 31, a RAM 32, a ROM 33, a nonvolatile memory 34, and the like. The CPU 31 controls the photographing apparatus 1 and peripheral devices. The RAM 32 temporarily stores various information. The ROM 33 stores various programs, initial values, and the like. The nonvolatile memory 34 is a non-transitory storage medium that can retain stored contents even when power supply is interrupted. For example, a hard disk drive, a flash ROM, and a USB memory that is detachably attached to the photographing apparatus 1 can be used as the nonvolatile memory 34. The non-volatile memory 34 stores an imaging control program for controlling main processing (see FIG. 3) described later. The nonvolatile memory 34 stores various information such as a captured tomographic image.

  In the present embodiment, a personal computer (hereinafter referred to as “PC”) connected to the measurement unit 10 is used as the control unit 30. However, the measurement unit 10 and the control unit 30 may be integrated as one device without using a PC. The control unit 30 may be configured by a plurality of control units (that is, a plurality of processors). For example, the control unit 30 of the photographing apparatus 1 may be configured by a first control unit provided in the PC and a second control unit provided in the measurement unit 10. In this case, for example, the first control unit of the PC may instruct the second control unit to start and end shooting based on the operation of the operation unit connected to the PC. The second control unit may control the operations of the measurement light source 11, the aiming light source 12, the motor 18 and the like according to instructions from the first control unit. Further, the image generation processing based on the interference signal may be performed by either the first control unit or the second control unit.

  Peripheral devices such as a display unit 41, an operation unit 42, and a surgical microscope 46 are electrically connected to the control unit 30. The display unit 41 displays a tomographic image, which will be described later. The display unit 41 may be a PC display or a display dedicated to the photographing apparatus 1. A plurality of displays may be used in combination. The operation unit 42 is a device for recognizing various operation instructions. For the operation unit 42, for example, at least one of a mouse, a joystick, a keyboard, a touch panel, and the like may be used. These may be operated by an assistant who assists the work from a location away from the worker. Further, for example, as the operation unit 42 to which an operation instruction from an operator is input, a switch (not shown) is provided in the probe 2, a voice recognition device for recognizing a voice from the operator, or an operator's gesture A device for recognizing may be provided.

  In the present embodiment, the control unit 30 also serves as an image forming unit that forms a tomographic image based on a signal from the detector 19. In this case, for example, the control unit 30 obtains a depth profile (A scan) by performing Fourier transform on the signal from the detector 19 and arranges the obtained depth profiles for each scanning position. Dimension OCT data (for example, B scan image) is generated. In this embodiment, since scanning is performed around the axis of the probe 2, each depth profile is expressed by polar coordinates where the origin is placed on the axis of the probe 2. The control unit 30 may acquire the two-dimensional OCT data of the subject expressed by the polar coordinates. Further, the two-dimensional OCT data may be tomographic image data expressed by polar coordinates, or may be tomographic image data expressed by orthogonal coordinates. For a conversion method from polar coordinate data to orthogonal coordinate data, see, for example, Japanese Patent Application Laid-Open No. 2015-104582 by the present applicant.

  The surgical microscope 46 magnifies and displays the inside of the subject (the eye E in this embodiment) during surgery, during diagnosis, or during these exercises (taken and magnified in this embodiment). The operator performs surgery, diagnosis, or training thereof while looking into the surgical microscope 46 (in the present embodiment, these are collectively referred to as “work”). In the present embodiment, the control unit 30 can acquire an image photographed by the surgical microscope 46 and display the image on the display unit 41. During the work, the worker's assistant or the like can check the work status and the like by checking the image displayed on the display unit 41. Note that the present disclosure can be realized without using the surgical microscope 46. For example, an observation optical system for taking an image inside the subject may be provided in the measurement unit 10. In this case, the operator can work while confirming the image photographed by the observation optical system. Further, the present disclosure can be applied even when the operator gazes near the tip of the probe 2 with the naked eye.

<2. Explanation of operation>
With reference to FIGS. 3 to 11, the operation of the photographing apparatus 1 will be described.

<Acquisition of B-scan image>
The control unit 30 turns on the measurement light source 11 to irradiate the measurement light from the deflection unit 71 and controls the motor 18 to rotate the fiber 4 at a constant speed. Thereby, the measurement light is scanned on the eye E. The control unit 30 acquires two-dimensional OCT data (for example, a B-scan image) based on a signal output from the detector 19 as the measurement light is scanned. For example, the two-dimensional OCT data may be formed based on a signal output from the detector 19 as a result of scanning the measurement light from one end to the other end of the transmission region 63. In the present embodiment, for each rotation of the fiber 4, the signal from the detector 19 is collected for a predetermined period based on the timing at which the signal from the rotation detection sensor 18a is obtained, and is collected during the predetermined period. Two-dimensional OCT data is constructed based on the signal.

  Here, FIG. 3 shows an example of two-dimensional OCT data acquired by the apparatus having the above configuration. FIG. 3 is a tomographic image represented by polar coordinates. Reference numeral 101 denotes a reflected image of the light shielding member 61, reference numeral 105 denotes an image of the subject (fundus), and 110 denotes an internal reflection image. The internal reflection image 110 is an image based on reflection at a portion having a different refractive index inside the probe 2. For example, an internal reflection image 110 may be generated by reflection at the fusion surface between the fiber 4 and a lens (not shown).

  Here, since the positional relationship between the deflecting unit 71 and the light shielding member 61 is constant, the reflected image 101 of the light shielding member 61 shows a certain depth. Further, the internal reflection location that generates the internal reflection image 110 also has a fixed positional relationship with the deflecting unit 71. Therefore, the internal reflection image 110 is formed at a position spaced apart from the reflection image 101 of the light shielding member 61 by a certain distance. Note that the internal reflection image 110 is not necessarily formed in a deeper area than the reflection image 101. Depending on the design of the probe 2, it may be formed in a region shallower than the reflected image 101.

  By the way, every time the fiber 4 is exchanged (every time the probe 2 is exchanged), the optical path length difference between the measurement light and the reference light changes due to an error in the length of the fiber 4, and as a result, in the tomographic image The position where the images 101, 105, 110 are formed moves up and down. Therefore, the control unit 30 according to the present embodiment sets the optical path length so that at least one of the reflected image 101 of the light shielding member 61 and the internal reflected image 110 is formed in a predetermined depth region in the tomographic image. The difference changing unit 20 is controlled to adjust the optical path length difference. For example, as shown in FIG. 3, the optical path length difference may be adjusted so that the reflected image 101 is arranged in a predetermined depth region 102 above the tomographic image. Thereby, the imaging range of the tomographic image in the depth direction is corrected to a certain range with reference to the position of the reflected image 101. As a result, the photographing apparatus 1 can photograph a range in a certain depth direction as a tomographic image.

<Acquisition of 3D OCT data>
As the probe 2 is moved with respect to the eye E, two-dimensional OCT data at different scanning lines is acquired by the control unit 30 as needed. As shown in FIG. 4, the control unit 30 arranges a plurality of two-dimensional OCT data in different scanning lines in time series. Thereby, the three-dimensional OCT data of the eye E is generated and acquired. As shown in FIG. 5 and the like, the three-dimensional OCT data may be a three-dimensional graphic that three-dimensionally shows the structure of the tissue of the fundus (subject). For example, the three-dimensional OCT data may be formed by arranging a plurality of two-dimensional OCT data in a direction orthogonal to both the depth direction and the scanning direction (for example, the depth direction of the tomographic image). The three-dimensional OCT data may be formed from, for example, a plurality of two-dimensional OCT data stored in advance in the nonvolatile memory 34 in conventional imaging. Further, the three-dimensional OCT data may be formed by sequentially arranging two-dimensional OCT data acquired in real time.

  Note that the three-dimensional graphic shown in FIG. 5 is expressed by polar coordinates. That is, it is formed by arranging a plurality of tomographic images expressed by polar coordinates. Note that the control unit 30 may form a three-dimensional graphic represented by orthogonal coordinates. This three-dimensional graphic can be formed by arranging a plurality of tomographic images represented by orthogonal coordinates. In the three-dimensional graphic expressed by polar coordinates, for example, even when a flat test object is imaged, the image of the test object is curved in the depth direction. On the other hand, the control unit 30 may generate a three-dimensional graphic expressed by orthogonal coordinates. In the three-dimensional graphic represented by the Cartesian coordinates, the above bending is suppressed (see FIG. 6).

  The acquisition period for acquiring the three-dimensional OCT data (the period for acquiring a plurality of two-dimensional OCT data constituting the three-dimensional OCT data) may be constant for each acquisition or may be changed as appropriate for each acquisition. It may be possible. The acquisition period may be started (and ended) based on a predetermined operation input to the operation unit 42.

<Removal of reflection image and internal reflection image of light shielding member>
Here, if each tomographic image constituting the three-dimensional graphic includes a reflection image by the probe 2, an image 205 of the subject (eye E) in the three-dimensional graphic is reflected by the reflection image 201 by the probe 2. In some cases, the image 205 of the subject may be difficult to grasp due to being obstructed by 210. Reflected images 201 and 210 by the probe 2 in this embodiment are reflected images generated by the structure of the probe 2. For example, the reflection image 201 by the light shielding member 61 and the internal reflection image 210 are mentioned. In the tomographic image shown in FIG. 3, the reflected images 101 and 110 correspond to each other.

  For example, in the three-dimensional graphic expressed by polar coordinates (see FIG. 5), the reflected image 201 by the light shielding member 61 is formed above the subject image 205 (position closer to the probe 2 with respect to the depth direction). The For this reason, there is a possibility that the reflected image 201 makes it difficult to confirm the image 205 of the subject. Further, in the three-dimensional graphic (see FIG. 6) expressed by orthogonal coordinates, for example, the internal reflection image 210 is formed so as to surround the image 205 of the subject. For this reason, the image 205 of the subject may be difficult to confirm due to the internal reflection image 210.

  On the other hand, the control unit 30 forms three-dimensional OCT data from which the reflection images 201 and 210 by the probe 2 are removed (see the three-dimensional graphics in FIGS. 7 and 8). In the present embodiment, at least one of the reflection image 201 and the internal reflection image 210 by the light shielding member 61 is removed. Such three-dimensional OCT data is obtained by removing the reflected images 101 and 110 by the probe 2 and removing the reflected images 101 and 110 by the probe 2 from each two-dimensional OCT data (see FIG. 3). It may be formed by arranging two-dimensional OCT data. Here, when the reflected image 101 by the probe 2 is formed in a predetermined depth region, the reflected image 101 by the probe 2 may be removed by deleting the information of the depth region.

  In the present embodiment, as a result of the control for adjusting the optical path length difference between the measurement light and the reference light, the reflected image by the probe 2 (at least one of the reflected image 101 of the light shielding member 61 and the internal reflected image 110). ) Are formed in a predetermined depth region in the two-dimensional OCT data. Therefore, the reflected images 101 and 110 by the probe 2 may be removed by deleting the information in this depth region.

  Moreover, the control part 30 may perform the detection process of the reflected images 101 and 110 by the probe 2 with respect to each two-dimensional OCT data, and may remove the reflected image detected by the detection process. For example, as shown in FIG. 3, the internal reflection image 110 spreads across the left and right regions without any breaks in each tomographic image expressed in polar coordinates. Therefore, for example, the internal reflection image 110 is detected in consideration of signal connectivity in the tomographic image (connectivity of pixels constituting the internal reflection image 110), and the detected internal reflection image 110 is removed from the two-dimensional OCT data. The control unit 30 may perform the process.

<Noise removal>
In addition, speckle noise may occur in a region deeper than the light shielding member 61 in each two-dimensional OCT data. It can be considered that speckle noise makes it difficult to obtain appropriate two-dimensional OCT data and three-dimensional OCT data.

  On the other hand, in this embodiment, speckle noise is removed using an image processing filter. The parameters of the image processing filter (for example, epsilon filter) may be adjusted according to noise in the two-dimensional OCT data acquired sequentially, or may be adjusted in advance. Note that this parameter may be set to an optimum value by applying a filter whose parameter is changed by trial and error to the two-dimensional OCT data including the fundus image. At this time, the noise removal effect is confirmed based on statistical information (for example, a histogram) of an image in a region (region 106 in FIG. 3) where the image of the subject does not occur in the two-dimensional OCT data. May be. Speckle noise can be suppressed by applying such a filter.

<Contrast enhancement>
Also, depending on the acquisition conditions, good contrast may not be obtained in the subject image 205. Therefore, the control unit 30 detects contrast in the image 205 of the subject from the two-dimensional OCT data, and performs contrast enhancement processing for increasing the contrast in the two-dimensional OCT data when the detected contrast is equal to or less than the threshold value. It may be.

<Input of selection instruction regarding probe movement conditions and correction of 3D OCT data>
In the present embodiment, based on a plurality of two-dimensional OCT data acquired by the control unit 30 along with the movement of the probe 2 in a state where the probe 2 (more specifically, the needle 6) is inserted into the eye E to be examined, Tissue 3D OCT data is acquired.

  At this time, the movement of the probe with respect to the subject at the time of acquiring a plurality of two-dimensional OCT data is reflected in the three-dimensional OCT data. However, the movement of the probe 2 with respect to the eye E is not necessarily constant every time a plurality of two-dimensional OCT data is acquired. Nevertheless, if the formation of the 3D OCT data is performed under certain conditions, the structure of the tissue cannot be accurately reproduced in the 3D OCT data. For example, it is considered that a difference in the movement condition is caused by any difference in the content of the work, the desired image quality, and the operator who moves the probe 2 or the like. Here, as movement conditions, for example, when acquiring a plurality of two-dimensional OCT data that is the basis of the three-dimensional OCT data, the movement amount of the probe 2, the movement speed of the probe 2, and the movement of the probe 2 in the movement of the probe 2 At least one of time. Also, the movement conditions such as the direction in which the probe 2 is moved with respect to the scanning line may be different each time a plurality of two-dimensional OCT data is acquired.

  If the arrangement interval of each two-dimensional OCT data in the three-dimensional OCT data and the length of the moving direction of the probe 2 in the three-dimensional OCT data are always fixed regardless of the movement conditions, the three-dimensional OCT It is conceivable that the scale in the data regarding the moving direction of the probe 2 changes for each three-dimensional OCT data. Also, if the direction in which a plurality of two-dimensional OCT data is arranged in the three-dimensional OCT data is fixed in a direction perpendicular to the image, the probe 2 is moved in a direction inclined with respect to the scanning line, and each When two-dimensional OCT data is acquired, it is conceivable that an image of a tissue is crushed obliquely in the three-dimensional OCT data.

  On the other hand, in the imaging apparatus 1 of the present embodiment, a selection instruction from the operator regarding the movement condition of the probe 2 when acquiring a plurality of two-dimensional OCT data that is the basis of the three-dimensional OCT data is given by the control unit 30. Accepted. When the control unit 30 forms the three-dimensional OCT data, or the control unit 30 selects the relative positional relationship of each two-dimensional OCT data with respect to the three-dimensional OCT data formed in advance. It adjusts based on the movement condition according to. In other words, the control unit 30 arranges the relative positional relationship of the two-dimensional OCT data while adjusting the relative positional relationship based on the movement condition of the probe 2, so that the relative tertiary of the two-dimensional OCT data is adjusted. Form original OCT data. The three-dimensional OCT data may be formed by a plurality of two-dimensional OCT data arranged along the curvature of the retina. The curvature of the retina may be, for example, a value (estimated value) obtained from the axial length information of the eye E obtained by an axial length measuring device.

  In the present embodiment, the control unit 30 receives a selection instruction based on a signal output from the operation unit 42 when a predetermined operation on the operation unit 42 is performed by the operator as a selection operation of the movement condition. The selection instruction may be information for defining a movement condition. As a value for determining the movement condition (that is, an example of a selection instruction), the movement amount of the probe 2 in the movement of the probe 2 when acquiring a plurality of two-dimensional OCT data as a basis of the three-dimensional OCT data, It may be a value indicating at least one of the movement speed and the movement time of the probe 2. Further, it may be at least one of the number of two-dimensional OCT data acquired during the movement period and the arrangement interval of the two-dimensional OCT data in the three-dimensional OCT data. Further, for example, it may be information indicating the inclination of the moving direction of the probe 2 with respect to the scanning line.

  The selection instruction may be input to the apparatus by a keyboard and a mouse which are an example of the operation unit 42, or may be input by a method other than this. For example, an input operation for designating at least a movement start position and an end position of the probe 2 for acquiring three-dimensional OCT data on a front image of the fundus Er photographed by the surgical microscope 46 or the like is performed by a touch panel, a mouse, or the like. By being performed via either, the distance between the movement start position and the end position may be input to the apparatus as a selection instruction indicating the movement amount. When not only the movement start position and the end position but also the trajectory of the probe 2 in the middle is input, the length of the trajectory may be acquired by the control unit 30 as a selection instruction indicating the movement amount.

  The timing at which the control unit 30 receives a selection instruction for adjusting the three-dimensional OCT data may be a time point before a plurality of two-dimensional OCT data constituting the three-dimensional OCT data is acquired. That is, the control unit 30 determines each two-dimensional OCT data in the three-dimensional OCT data based on the selection instruction received before the movement of the probe 2 when acquiring a plurality of two-dimensional OCT data that is the basis of the three-dimensional OCT data. You may adjust the relative positional relationship of OCT data. In this case, for example, the operator selects an instruction for moving the probe 2 under an intended moving condition in consideration of factors such as desired image quality, operator experience, work content, etc. in the three-dimensional OCT data. Is considered to be entered. Prior to acquiring a plurality of two-dimensional OCT data, since an appropriate movement condition is assumed by the operator, it is difficult for the operator to be confused as to how to move the probe 2 in the operation.

  The timing at which the control unit 30 receives a selection instruction for adjusting the three-dimensional OCT data may be a point in time after a plurality of two-dimensional OCT data constituting the three-dimensional OCT data is acquired. That is, the control unit 30 determines each two-dimensional OCT data in the three-dimensional OCT data based on the selection instruction received after the movement of the probe 2 when acquiring a plurality of two-dimensional OCT data that is the basis of the three-dimensional OCT data. You may adjust the relative positional relationship of data. In this case, the positional relationship between the two-dimensional OCT data constituting the three-dimensional OCT data can be adjusted afterwards according to the actual movement of the probe 2.

  Of course, the control unit 30 may be able to accept a selection instruction for adjusting the three-dimensional OCT data at each time point before and after acquiring a plurality of two-dimensional OCT data constituting the three-dimensional OCT data. . In this case, when the control unit 30 receives a selection instruction at each time point before and after acquiring a plurality of two-dimensional OCT data, for example, three-dimensional OCT data adjusted based on the selection instruction at each time point is obtained. Each may be generated and stored in a memory (for example, the nonvolatile memory 34). In this case, the selection instruction acquired at a later time may be prioritized. That is, the positional relationship between the two-dimensional OCT data constituting the three-dimensional OCT data may be adjusted based on the movement condition determined by the selection instruction acquired at a later time.

  As a selection instruction, at least one of the movement amount of the probe 2, the movement speed of the probe 2, and the movement time of the probe 2 in the movement of the probe 2 when acquiring a plurality of two-dimensional OCT data that is the basis of the three-dimensional OCT data. Alternatively, when at least one of the acquisition number of the two-dimensional OCT data during the movement period of the probe 2 and the arrangement interval of the two-dimensional OCT data in the three-dimensional OCT data is acquired, the control unit 30 At least the scale relating to the moving direction of the probe 2 in the three-dimensional OCT data is adjusted. That is, the arrangement interval of each two-dimensional OCT data in the three-dimensional OCT data is any one of the movement conditions (that is, the movement amount of the probe 2, the movement speed of the probe 2, and the time for moving the probe 2) determined by the selection instruction. ) (FIG. 9 (a) → FIG. 9 (b)). As a result, it is possible to form three-dimensional OCT data that makes it easy to grasp the structure of the tissue.

  For example, when the movement amount of the probe 2 is acquired as a selection instruction, the control unit 30 sets and sets a length corresponding to the movement amount as the length related to the movement direction of the probe 2 in the three-dimensional OCT data. The three-dimensional OCT data may be formed so that the two-dimensional OCT data is arranged at substantially equal intervals in the range of the length.

  Further, for example, when the moving speed of the probe 2 is acquired as a selection instruction, the interval between the acquisition positions of the two-dimensional OCT data is calculated from the frame rate related to the acquisition of the two-dimensional OCT data and the moving speed. The control unit 30 may form the three-dimensional OCT data so that each two-dimensional OCT data is arranged at a calculated interval (for example, movement speed / frame rate).

  Further, for example, when a time for moving the probe 2 is acquired as a selection instruction, the length of the probe 2 in the moving direction of the three-dimensional OCT data assuming that the moving speed of the probe 2 is a predetermined speed. And three-dimensional OCT data may be formed within a set length range. Also, assuming that the amount of movement of the probe 2 is a predetermined fixed amount, the interval of each two-dimensional OCT data in the three-dimensional OCT data is adjusted so that the probe 2 is arranged at a substantially equal interval in the fixed amount range. May be.

  Further, for example, information indicating the inclination of the moving direction of the probe 2 with respect to the scanning line may be input via the operation unit 42 as a selection instruction. For example, an angle corresponding to the inclination may be input via a keyboard and a mouse. Further, for example, an input operation for designating the direction of the scanning line and the moving direction of the probe 2 on the front image of the eye E to be imaged by the surgical microscope 46 or the like is performed via any one of the touch panel and the mouse. As a result, information corresponding to the movement amount may be input. Of course, the input method may be a method other than the above.

  When information indicating the inclination of the moving direction of the probe 2 with respect to the scanning line is acquired as a selection instruction, the control unit 30 causes each two-dimensional OCT data to be in a direction corresponding to the inclination from the adjacent two-dimensional OCT data. The positional relationship in the left-right direction (scanning direction) of each two-dimensional OCT data in the three-dimensional OCT data may be adjusted so as to be displaced (for example, FIG. 10A → FIG. 10B). In addition, the arrangement interval of the two-dimensional OCT data (in other words, the positional relationship in the front-rear direction) may be adjusted. As a result, it is reduced that the tissue image is obliquely collapsed in the three-dimensional OCT data.

  In the present embodiment, the operator can grasp the inclination of the moving direction of the probe 2 with respect to the scanning line by checking the moving direction of the probe 2 with respect to the aiming light when the probe 2 moves. For this reason, the selection instruction indicating the inclination of the moving direction of the probe 2 with respect to the scanning line is obtained by acquiring the positional relationship between the plurality of two-dimensional OCT data after the plurality of two-dimensional OCT data constituting the three-dimensional OCT data is once acquired. It may be obtained for adjusting.

<Correction of three-dimensional OCT data using detection result of acquisition position of two-dimensional OCT data>
In addition, the imaging apparatus 1 uses a wide-range image that is an eye image to be examined in a wider range than the three-dimensional OCT data for the movement of the probe 2 when acquiring a plurality of two-dimensional OCT data constituting the three-dimensional OCT data. It may be detected. Then, three-dimensional OCT data in which the positional relationship of each two-dimensional OCT data is adjusted based on the detection result may be formed.

  In the present embodiment, motion detection is typically performed by detection of acquisition positions for all or a part (at least two or more) of a plurality of two-dimensional OCT data constituting the three-dimensional OCT data. The acquisition position is detected based on a wide range image acquired (captured) simultaneously with the two-dimensional OCT data. Note that “simultaneous” here includes a case where the acquisition timing of the two images is different within a range in which the acquisition position of the two-dimensional OCT data can be substantially detected using a wide range image.

  The wide range image is used as a reference for arranging the two-dimensional OCT data. The wide range image may be, for example, a front image of the fundus Er or a wide range of three-dimensional OCT data. The wide range image may be, for example, an image of the entire tissue to be imaged. Such a wide-range image may be an image taken non-invasively. For example, the front image is obtained by non-invasive imaging such as a surgical microscope 46, a fundus camera, a scanning laser ophthalmoscope, etc. (that is, imaging is performed without inserting a probe unlike the imaging apparatus 1). You may acquire using a meter. Further, the three-dimensional OCT data may be acquired using an optical tomographic interferometer that performs noninvasive imaging. The image acquired using an apparatus other than the surgical microscope 46 may be an image acquired in advance before work, for example. In the case of the eye E, an image of the entire retina or an image of the entire eye E may be used. However, it is not always necessary to cover a wide range of the entire tissue, and any image having a sufficient width that includes the imaging range of the three-dimensional OCT data in the imaging apparatus 1 may be used.

<Detection of acquisition position based on aiming light>
The control unit 30 can detect the acquisition position of the two-dimensional OCT data using the wide range image in which the acquisition position of the two-dimensional OCT data is indicated by the aiming light. For example, a front image of the fundus Er acquired from the surgical microscope 46 and the like together with the two-dimensional OCT data can be used as a wide range image. As shown in FIG. 11, the acquisition position of the two-dimensional OCT data in the eye E can be detected as the position of the aiming light image 301 in the front image of the fundus Er acquired from the surgical microscope 46 together with the two-dimensional OCT data. . Therefore, for example, based on the aiming light image 301 in the front image acquired together with the two-dimensional OCT data, the relative positional relationship between the two-dimensional OCT data may be adjusted in the three-dimensional OCT data. More specifically, the control unit 30 obtains the irradiation position information of the aiming light with respect to the fundus Er (that is, the position information of the image 301) from the front image of the fundus Er acquired together with each two-dimensional OCT data. Detect as. Here, the aiming light image 301 is generated substantially perpendicular to the needle 6 of the probe 2. Therefore, the control unit 30 may detect the image 301 by detecting an edge perpendicular to the needle 6 from the front image. In this way, the acquisition position may be obtained.

  And the control part 30 forms the three-dimensional OCT data by which the relative positional relationship of each two-dimensional OCT data was adjusted based on the detected acquisition position. Based on the acquired information (that is, information indicating the acquisition position), the control unit 30, for example, the interval between the two-dimensional OCT data, the horizontal arrangement in each two-dimensional OCT data, and the depth in each two-dimensional OCT data You may adjust at least any one of arrangement | positioning of a direction, the direction of the tomographic plane of two-dimensional OCT data, etc. Furthermore, the scale in the scanning direction of each two-dimensional OCT data may be adjusted.

  Specifically, the control unit 30 may adjust the arrangement interval of each two-dimensional OCT data according to the interval of the irradiation position of the aiming light corresponding to each two-dimensional OCT data. Further, the arrangement in the left-right direction in each two-dimensional OCT data may be adjusted in accordance with the amount of displacement of the irradiation position in the left-right direction (direction intersecting the moving direction of the probe 2). Further, the position in the depth direction where the image of the eye E is formed in the two-dimensional OCT data differs according to the positional relationship between the probe 2 and the eye E in the depth direction. Here, the image 301 formed on the fundus by the aiming light on the fundus becomes larger as the probe 2 and the eye E to be examined are separated. Accordingly, the control unit 30 may obtain the relative position in the depth direction between the probe 2 and the eye E for the front image corresponding to each two-dimensional OCT data from the size of the image 301 in the front image. . Then, the control unit 30 corrects the position in the depth direction of the image of the eye E in the two-dimensional OCT data according to the relative position in the depth direction acquired from the front image corresponding to the two-dimensional OCT data, Three-dimensional OCT data may be formed by arranging two-dimensional OCT data subjected to such correction. The correspondence relationship between the size of the image 301 in the front image and the relative position in the depth direction between the probe 2 and the eye E to be examined is obtained in advance by calibration or simulation, and the control unit 30 in the correction process. However, the result may be referred to as either a lookup table or a function.

  In addition, the surface imaged as two-dimensional OCT data is not always perpendicular to the fundus surface. It is also conceivable that a plane inclined with respect to the fundus surface is acquired. Here, the inclination with respect to the fundus surface in the plane of the two-dimensional OCT data is reflected in the image of the aiming light. For example, the curvature of the aiming light image 301 changes according to the inclination. Therefore, the control unit 30 may obtain the curvature of the image 301 from the front image and acquire the inclination corresponding to the curvature (inclination of the plane of the tomographic image with respect to the fundus surface). And the control part 30 may form 3D OCT data by arranging each 2D OCT data with the inclination acquired from the front image corresponding to each 2D OCT data, respectively. Note that the correspondence between the curvature of the image 301 and the inclination of the surface of the tomographic image is obtained in advance by calibration or simulation, and the control unit 30 obtains the result in the above correction processing, such as a look-up table and a function. You may make it referable as either.

<Detection of acquisition position based on a wide range of 3D OCT data>
Also, the acquisition position of the two-dimensional OCT data is acquired by the control unit 30 by comparing a wide-range image, which is an image of the eye E having a wider range than the three-dimensional OCT data, with at least a part of the three-dimensional OCT data. May be. The part of the three-dimensional OCT data may be, for example, one or more two-dimensional OCT data constituting the three-dimensional OCT data, or may be a part of the two-dimensional OCT data. Further, for example, an image on a plane along a layer in the three-dimensional OCT data may be used. Further, it may be a part thereof. For example, the image on the plane along the layer may be a plane image of the fundus surface. According to this method, the acquisition position of the two-dimensional OCT data can be detected (acquired) without necessarily using an observation device such as the surgical microscope 46. Based on the acquired information, the control unit 30 can determine, for example, the interval between the two-dimensional OCT data, the horizontal arrangement in each two-dimensional OCT data, the arrangement in the depth direction in each two-dimensional OCT data, and the two-dimensional OCT data. At least one of the orientation of the tomographic plane, etc. may be adjusted. Furthermore, the scale in the scanning direction of each two-dimensional OCT data may be adjusted.

  The control unit 30 detects a part of the wide-range image that includes a part of the three-dimensional OCT data acquired by the imaging apparatus 1 from the wide-range image using the partial information of the three-dimensional OCT data. . For example, when the three-dimensional information of the eye is included in the wide-range image (for example, when the wide-range image is configured by the three-dimensional OCT data), the control unit 30 acquires the two images acquired by the imaging device 1. The position of the two-dimensional OCT data on the wide-range image may be detected by matching the dimensional OCT data with the wide-range image. Then, the three-dimensional OCT data may be formed by adjusting the positional relationship of the two-dimensional OCT data so that the two-dimensional OCT data is arranged in the positional relationship at the obtained position. Note that the matching between the two-dimensional OCT data and the wide-range image may be a three-dimensional extraction from the wide-range image where the degree of coincidence with the two-dimensional OCT data is high.

  In this way, the positional relationship of the two-dimensional OCT data constituting the three-dimensional OCT data is adjusted based on the acquisition position of the two-dimensional OCT data detected by the imaging apparatus 1 using the wide range image. Therefore, also in this case, it is possible to obtain good three-dimensional OCT data adjusted according to the above-described movement conditions for each photographing. Further, in this case, when acquiring a plurality of two-dimensional OCT data constituting the three-dimensional OCT data, if the direction and moving speed of the probe 2 change during the process, the eye E to be inspected during imaging The positional relationship between the two-dimensional OCT data can be appropriately adjusted even when the probe 2 moves relative to the eye E due to movement or camera shake of the operator. As a result, good three-dimensional OCT data is easily obtained.

  As described above, the description has been given based on the embodiment, but the present disclosure is not necessarily limited to the above-described embodiment, and includes various modifications that can be implemented based on ordinary knowledge of those skilled in the art.

  For example, in the above-described embodiment, the case where the entire probe 2 is moved by the operator's hand (that is, the probe 2 is moved relative to the subject while being grasped by the operator) has been described. It is not a thing.

  For example, the technique of the above embodiment is applied to a case where a plurality of two-dimensional OCT data as a basis of the three-dimensional OCT data is acquired by moving a part of the probe 2 with respect to the subject. Can be applied. That is, the technique of the above embodiment may be applied when three-dimensional OCT data is obtained by moving at least a part of the probe 2 with respect to the subject. The partial movement of the probe 2 may be, for example, movement of the deflection unit 71 in the axial direction of the fiber 4. In this case, an actuator (not shown) built in the probe 2 may move the deflecting unit 71 in the axial direction of the fiber 4.

  In this case, as a selection instruction from the operator, a selection instruction regarding a movement condition (speed, movement amount, movement time, etc.) for a partial movement of the probe (that is, movement of the deflecting unit 71 in the axial direction of the fiber 4). Is received by the control unit 30. As a result of receiving such a selection instruction, the control unit 30 adjusts the positional relationship of each two-dimensional OCT data in the three-dimensional OCT data based on the movement condition according to the selection instruction. In addition, when a selection instruction is received before acquiring the two-dimensional OCT data, the control unit 30 acquires each two-dimensional OCT data by controlling the driving of the actuator based on the movement condition according to the selection instruction. May be. In other words, control for acquiring a plurality of two-dimensional OCT data may be performed under the movement conditions desired by the worker.

  In addition, for example, when the probe 2 is moved by a robot, the technique of the above embodiment may be applied. Further, when the probe 2 that two-dimensionally scans the measurement light with respect to the fundus surface is used, the technique of the above embodiment may be applied.

  Moreover, although the deflection | deviation part 71 of the probe 2 demonstrated as a structure rotated with the fiber 4 in the said embodiment, it is not necessarily restricted to this. For example, more specifically, the deflecting unit 71 may be configured to oscillate laser light within a certain range, such as a galvanometer mirror and an AOM (acousto-optic element).

DESCRIPTION OF SYMBOLS 1 Optical tomography apparatus 2 Probe 11 Light source 19 Detector 30 Control part E Eye to be examined

Claims (13)

The light output from the light source is divided into measurement light and reference light, the measurement light is irradiated onto the subject via a probe inserted into the subject, and the measurement light is repeatedly scanned, and the measurement light An optical tomography apparatus for detecting interference between the reflected light of the light and the reference light by a detector,
Along with the movement of at least a part of the probe with respect to the subject, two-dimensional OCT data of the subject in a plurality of scanning lines is formed based on signals from the detector, Image forming means for arranging the two-dimensional OCT data of the subject to obtain the three-dimensional OCT data of the subject,
An instruction receiving means for receiving a selection instruction from an operator regarding a movement condition of the probe when acquiring a plurality of two-dimensional OCT data that is a basis of the three-dimensional OCT data;
The optical tomography apparatus, wherein the image forming unit adjusts a relative positional relationship of each two-dimensional OCT data in the three-dimensional OCT data based on the movement condition.   The optical tomography apparatus according to claim 1, wherein the instruction selection unit receives the selection instruction related to a movement condition of the entire probe when the entire probe is moved with respect to the subject. The instruction receiving means relates to at least any of the movement conditions of movement amount, movement speed, and movement time in the movement of at least a part of the probe when acquiring a plurality of two-dimensional OCT data as a basis of the three-dimensional OCT data. Accepting the selection instruction;
The optical tomography apparatus according to claim 2, wherein the image forming unit adjusts an arrangement interval of each two-dimensional OCT data in the three-dimensional OCT data based on the movement condition.   The instruction receiving means indicates information indicating the movement condition, information indicating the number of acquired two-dimensional OCT data during the movement period of the probe, and an arrangement interval of the two-dimensional OCT data in the three-dimensional OCT data. The optical tomography apparatus according to claim 3, wherein at least one of information is received as the selection instruction.   The image forming means is based on the selection instruction received by the instruction receiving means before the movement of the probe when acquiring a plurality of two-dimensional OCT data that is a basis of the three-dimensional OCT data. 5. The optical tomography apparatus according to claim 1, wherein the relative positional relationship between the two-dimensional OCT data in the original OCT data is adjusted. The instruction receiving unit indicates a movement condition related to an inclination of a moving direction of the probe with respect to a scanning line by the measurement light when acquiring a plurality of two-dimensional OCT data as a basis of the three-dimensional OCT data as the selection instruction. Accept information,
The image forming means is configured so that each two-dimensional OCT data in the three-dimensional OCT data is arranged so that each two-dimensional OCT data is shifted from a neighboring two-dimensional OCT data in a direction corresponding to the inclination. The optical tomographic imaging apparatus according to claim 1, wherein the positional relationship in the left-right direction is adjusted. The instruction accepting unit displays an image showing the fundus of the eye to be examined on a display, and acquires information on a movement locus of the probe on the image as the selection instruction.
The optical tomography apparatus according to claim 1, wherein the image forming unit adjusts a relative positional relationship between the two-dimensional OCT data in the three-dimensional OCT data according to the movement locus. Detecting means for detecting the acquisition position of each of the two-dimensional OCT data that is the basis of the three-dimensional OCT data from a wide-range image that is an image of a wide range of the subject compared to the three-dimensional OCT data;
8. The light according to claim 1, further comprising: an adjustment unit that adjusts a relative positional relationship between the two-dimensional OCT data in the three-dimensional OCT data based on an acquisition position detected by the detection unit. Tomographic imaging device. Aiming light irradiating means for irradiating the subject with aiming light indicating the position where the measurement light is irradiated, together with the measurement light, through the probe;
A front image acquisition means for acquiring a front image of the subject imaged by a front image imaging means and including a front image including an image of aiming light indicating an acquisition position of the two-dimensional OCT data; With
The detection means acquires the irradiation position of the aiming light in the front image acquired together with each two-dimensional OCT data as the acquisition position,
The adjusting means is arranged so that each of the two-dimensional OCT data in the three-dimensional OCT data is arranged so that each of the two-dimensional OCT data is arranged in a positional relationship at the irradiation position of the aiming light corresponding to each of the two-dimensional OCT data. The optical tomography apparatus according to claim 8, wherein the positional relationship is adjusted.   The detection means obtains the two-dimensional OCT data by matching the two-dimensional OCT data, which is a basis of the three-dimensional OCT data, with a wide range two-dimensional OCT data of a subject stored in advance in a memory. 9. The optical tomography apparatus according to claim 8, wherein the position is detected. The detection means detects a distance in the depth direction between the probe and the subject when acquiring a plurality of two-dimensional OCT data serving as a basis of the three-dimensional OCT data,
The adjusting unit adjusts the positional relationship in the depth direction of each two-dimensional OCT data in the three-dimensional OCT data so that each two-dimensional OCT data is arranged at a position corresponding to the distance in the depth direction. The optical tomography apparatus according to any one of claims 8 to 10.   The light according to claim 11, wherein the adjusting unit adjusts the magnification of each two-dimensional OCT data in the three-dimensional OCT data so that each two-dimensional OCT data has a magnification corresponding to a distance in a depth direction. Tomographic imaging device. The detection means further includes information corresponding to the inclination of the surface from which the two-dimensional OCT data is acquired with respect to the surface of the subject when acquiring a plurality of two-dimensional OCT data as a basis of the three-dimensional OCT data. Detect
The adjustment means adjusts the positional relationship of each two-dimensional OCT data in the three-dimensional OCT data so that the respective two-dimensional OCT data are arranged at respective inclinations with respect to the surface of the subject. The optical tomography apparatus according to any one of the above.