JP2020141763A - Ophthalmologic image processing program, ophthalmologic image processing method, and ophthalmologic imaging apparatus - Google Patents

Abstract

To provide an ocular fundus imaging apparatus 1 for describing morphological features present in each depth position in a color image of an eye to be examined.SOLUTION: An ocular fundus imaging apparatus 1 acquires a plurality of ocular fundus images taken by imaging optical systems 10 and 20 at mutually different focus positions for an imaging range on the ocular fundus, which are captured for each of a plurality of channels indicating mutually different wavelength components. An image processor 80 of the ocular fundus imaging apparatus 1 executes composite processing for compositing the plurality of ocular fundus images with mutually different focus positions and acquiring a monochrome composite image for each channel, and generates a multi-color ocular fundus image based on the monochrome composite images of a plurality of the channels.SELECTED DRAWING: Figure 2

Description

The present disclosure relates to an ophthalmic image processing program for processing an image of an eye to be inspected, an ophthalmic image processing method, and an ophthalmic imaging apparatus.

Conventionally, a color image of an eye to be inspected has been widely used in ophthalmic diagnosis and the like. For example, a fundus camera, an SLO device, and the like are known as devices for capturing a fundus image, which is one of ophthalmic images.

For example, Patent Document 1 states that laser light of three colors of red, blue, and green is simultaneously or selectively emitted from a light source as illumination light, and a multicolored fundus is based on the reflected light of the fundus of each color. An SLO device that produces an image is disclosed.

Japanese Unexamined Patent Publication No. 2016-059539

For example, the depth of light penetration in the tissue of the eye to be inspected, such as the fundus, varies from wavelength to wavelength. Therefore, it is considered that the optimum focus position in the eye to be inspected differs depending on the wavelength component of the illumination light. However, this point has not been taken into consideration in the conventional device.

For this reason, in a color image taken by a conventional device, for example, morphological features existing at each depth position are not always sufficiently described.

The present disclosure has been made in view of at least one of the problems of the prior art, and is a technique of satisfactorily describing the morphological features existing at each depth position in the color image of the eye to be inspected. Make it an issue.

The ophthalmic image processing program according to the first aspect of the present disclosure is a plurality of ophthalmic images captured at different focus positions with respect to one imaging range in the eye to be examined by being executed by a computer processor. , An acquisition step of acquiring a plurality of ophthalmic images taken for each of a plurality of channels showing different wavelength components, and a compositing process of synthesizing a plurality of the ophthalmic images having different focus positions to obtain a monochromatic composite image. The computer is made to execute a monochromatic composite step executed for each channel and a color composite step for generating a color composite image which is a multicolor ophthalmic image based on the monochromatic composite image of a plurality of channels.

The ophthalmic image processing method according to the second aspect of the present disclosure is a plurality of ophthalmic images taken at different focus positions with respect to one imaging range in the eye to be examined, and a plurality of channels showing different wavelength components. An acquisition step of acquiring a plurality of ophthalmic images taken for each channel, and a monochromatic compositing step of performing a compositing process of compositing a plurality of the ophthalmic images having different focus positions to obtain a monochromatic composite image for each channel. It includes a color composition step of generating a color composition image which is a multicolor ophthalmic image based on the monochromatic composition image of a plurality of channels.

The ophthalmologic imaging apparatus according to the third aspect of the present disclosure includes an imaging optical system that captures an ophthalmic image by irradiating an eye to be inspected with illumination light of a plurality of wavelengths, and a focus that is different from each other for one imaging range in the eye to be inspected. It has a control means and an image processing means for acquiring a plurality of ophthalmic images taken at a position for each of a plurality of channels showing different wavelength components by the shooting. The image processing means executes a compositing process for each channel to obtain a monochromatic composite image by synthesizing a plurality of ophthalmic images having different focus positions, and further, based on the monochromatic composite images of the plurality of channels, multi Generates a color composite image that is a color ophthalmic image.

According to the present disclosure, in a color image of an eye to be inspected, morphological features existing at each depth position can be well described.

It is a figure which shows the schematic structure of the fundus photography apparatus which concerns on embodiment. It is a figure which showed the procedure of the image processing method in 1st Example. It is a figure which showed the procedure of the image processing method in 2nd Example. It is a figure which illustrated the color composite image obtained by the image processing method of 3rd Example.

Hereinafter, embodiments according to the present disclosure will be described with reference to the drawings. For convenience, the processing contents of the "ophthalmic image processing program" and the "ophthalmic image processing method" according to the embodiment will be described below as being executed by the "fundus photography device" unless otherwise specified. ..

The fundus photography device is an example of an "ophthalmologic photography device". The fundus photography apparatus captures a frontal image of the fundus (hereinafter referred to as a fundus image) as an image of the eye to be inspected (ophthalmic image). However,
The "ophthalmologic imaging device" is not necessarily limited to imaging the fundus of the eye, and may image other parts such as the anterior segment of the eye to be inspected.

<Overall configuration>
The fundus photography device 1 (hereinafter abbreviated as “the device 1”) according to the embodiment includes at least the photographing optical systems 10 and 20 and the image processor (image processor) 80. By having the image processor 80, the present device 1 becomes a computer that executes various image processes. The image processor 80 may also be used by a processor that controls the operation of the entire device. The image processor 80 may be separate from the processor that controls the operation of the entire device. An ophthalmic image processing program may be stored in the memory accessible from the processor of the image processor 80.

As shown in FIG. 1, the apparatus 1 is roughly divided into an optical unit 1a and a control unit 1b. The photographing optical systems 10 and 20 are the optical unit 1a, and the image processor 80 is the control unit. Each may be stored in 1b. The control unit 1b has various memories 72 in addition to the processor (CPU) 71. The ophthalmic image processing program may be stored in the memory 72. Further, the operation unit 75 (user interface) may be connected to the control unit 1b. The operation unit 75 may be a pointing device such as a mouse and a touch panel, or may be another user interface. For example, a PC may be used as the control unit 1b.

Further, the present device 1 may have a monitor 90. For example, a captured fundus image is displayed on the monitor 90. In addition, various GUIs may be displayed on the monitor 90.

<Shooting optical system>
The photographing optical systems 10 and 20 capture a fundus image. In the present embodiment, the fundus image is a frontal image of the fundus. The photographing optical systems 10 and 20 include an irradiation optical system 10 and a light receiving optical system 20 (see FIG. 1).

The photographing optical systems 10 and 20 may be scanning optical systems. Further, for example, the photographing optical systems 10 and 20 may be cofocal optical systems. As an example, FIG. 1 shows a schematic configuration of photographing optical systems 10 and 20 using a scanning confocal optical system. In this case, the irradiation optical system 10 has an optical scanner 17 that collects the illumination light in a point shape or a line shape on the fundus, and scans the illumination light on the fundus by the optical scanner 17. The light receiving optical system 20 has at least a light receiving element 25. Further, the light receiving optical system 20 is provided with a harmful light removing portion (for example, a pinhole, a slit aperture, etc.) (not shown) at a fundus conjugate position. The harmful light removing unit guides the fundus reflected light from the area irradiated with the illumination light to the light receiving element 25, and removes the other parts. Then, as a result of successive light reception by the light receiving element 25, a front image of the fundus is acquired. In the line scan method, the light receiving element 25 may also serve as a harmful light removing unit. In this case, the line sensor used as the light receiving element 25 is arranged at the fundus conjugate position.

Further, the imaging optical system of the present device 1 is not necessarily limited to this, and may be a non-confocal system. An example of a non-confocal imaging optical system is an optical system of a general fundus camera.

The irradiation optical system 10 irradiates the fundus with illumination light from the light source 11. The irradiation light has a wavelength range corresponding to a plurality of primary color components. The illumination light may be visible light. The illumination light may be, for example, a plurality of monochromatic lights having different wavelengths from each other. Note that "monochromatic light" has a narrow meaning of light that cannot be decomposed into spectra, but is not necessarily limited to this in the present disclosure. The "monochromatic light" in the present disclosure may have a wavelength distribution width that can be treated as a specific one color in the technical field of the fundus photography apparatus. Further, the illumination light is not necessarily limited to this, and the illumination light may be white light.

The irradiation optical system 10 shown as an example in FIG. 1 includes a beam splitter 12, a lens 13a, an optical scanner 17, and an objective lens 19.

The beam splitter 12 combines and separates the optical paths of the irradiation optical system 10 and the light receiving optical system 20. The beam splitter 12 may be, for example, a perforated mirror, a half mirror, or another member.

The apparatus 1 has a lens 13a and a driving unit 13b as the focus adjusting unit 13. The focus adjusting unit 13 is used to change the focus position on the fundus in the depth direction. Further, as an example, the focus adjusting unit 13 of the present device 1 also serves as a diopter correction unit, and corrects the diopter of the eye to be inspected. In the photographing optical systems 10 and 20 shown in FIG. 1, the lens 13a is displaced along the optical axis based on the drive of the drive unit 13b. The focus position is changed with respect to the depth direction (Z direction) of the eye to be inspected according to the position of the lens 13a. In this embodiment, the position of the lens 13a is controlled by the processor 71.

The focus adjusting unit 13 is not limited to the one provided with the moving lens 13a. For example, the focus adjusting unit 13 may have a variable focus lens such as a liquid crystal lens, or may include an optical system capable of changing the optical path length. In any case, the focus adjusting unit 13 includes an optical element that can be arranged in the optical path of the photographing optical systems 10 and 20, and a driving unit (actuator) that drives the optical element.

The optical scanner 17 is used to scan the illumination light emitted from the light source 11 on the fundus. When a spot-shaped luminous flux is projected onto the fundus, the optical scanner 17 scans the light in two different directions. At this time, the optical scanner 17 may include a first optical scanner for main scanning and a second optical scanner for sub-scanning. Further, the optical scanner 17 may be a device having two degrees of freedom (for example, MEMS or the like). When a line-shaped light beam is projected onto the fundus, the optical scanner 17 scans at least in a direction intersecting the longitudinal direction of the cross section of the line-shaped light beam. In each case, as the optical scanner, any one of a galvano mirror, a polygon mirror, a resonant scanner, a MEMS, an acoustic optical element (AOM), and the like may be appropriately selected.

The objective lens 19 is an objective optical system of the present device 1. The objective lens 19 is used to guide the laser beam scanned by the optical scanner 17 to the fundus Er. The objective lens 19 forms a turning point P at the position of the exit pupil. At the turning point P, the illumination light that has passed through the optical scanner 17 is swirled.

In the present disclosure, "conjugation" is not necessarily limited to a perfect conjugation relationship, but includes "substantially conjugation". That is, the case where the fundus image is arranged so as to be deviated from the perfect conjugate position within a range permitted in relation to the purpose of use (for example, observation, analysis, etc.) is also included in the "conjugation" in the present disclosure.

The laser light that has passed through the optical scanner 17 passes through the objective lens 19 and is irradiated to the fundus Er through the turning point P. By turning the illumination light around the turning point P, the illumination light is scanned on the fundus Er. The illumination light applied to the fundus Er is reflected at the condensing position (for example, the surface of the retina). The fundus reflected light of the illumination light is emitted from the pupil as parallel light.

Next, the light receiving optical system 20 will be described. The light receiving optical system 20 has one or more light receiving elements. For example, the light receiving optical system 20 shown in FIG. 1 has a light receiving element 25 as an example. In FIG. 1, the fundus reflection light of the illumination light is guided to the light receiving element 25 by being reflected by the beam splitter 12 (via the objective lens 19 to the lens 13a) in the optical path at the time of projection. The signal from the light receiving element 25 is input to the image processor 80, and as a result, a fundus image is generated by the image processor 80. In the light receiving optical system 20, a plurality of light receiving elements 25 may be provided for each wavelength. In this case, a plurality of fundus reflected lights having different wavelengths may be simultaneously received by the plurality of light receiving elements 25. Further, a plurality of fundus reflected lights having different wavelengths may be received by one light receiving element 25 in a time division manner (in other words, at different timings). As the light receiving element 25, any one of a point light receiving element, a one-dimensional image sensor (line sensor), a two-dimensional image sensor, and the like may be used. Which one is adopted is appropriately selected according to the shooting method.

In the present embodiment, a multicolor fundus image (hereinafter, abbreviated as “MC fundus image”) can be photographed by the photographing optical systems 10 and 20 as described above. In the MC fundus image, each pixel has a plurality of color information. When taking the MC fundus image, the fundus image for each channel (for each wavelength component) may be acquired and generated based on the signal from the light receiving element 25. In addition, the MC fundus image may be generated and acquired based on the fundus images of a plurality of channels. In this embodiment, various fundus images are generated by the image processor 80.

When capturing an MC fundus image, in the present embodiment, illumination light consisting of three monochromatic lights of R (red), G (green), and B (blue) is emitted and received by the photographing optical systems 10 and 20. To. The depth of light penetration in the retina is different for each wavelength. Of the three colors of light, B (blue) light reaches the surface of the retina. R (red) light reaches deep into the retina. The G (green) light reaches an intermediate depth between the B (blue) light and the R (red) light. Therefore, it is possible to satisfactorily photograph layers having different depths by illuminating three colors of R (red), G (green), and B (blue). At this time, IR (infrared) light may be additionally irradiated to the fundus of the eye, either additionally or in place of R (red) light. In the present embodiment, when the MC fundus image is taken, light of three or four colors is irradiated to the fundus, but the present invention is not necessarily limited to this. For example, the light applied to the fundus may be two colors or five or more colors. Further, the above color combination is only an example, and an MC fundus image may be taken by another color combination.

Further, a monochrome fundus image, which is a kind of fundus image, may be captured by the photographing optical systems 10 and 20. The monochrome fundus image may be, for example, a fundus image based on any one of R (red), G (green), and B (blue). Further, it may be an observation image based on the monochrome fundus image IR (infrared) light.

By the way, the depth of light penetration in the retina is different for each wavelength. Since there is a trade-off relationship between the optical depth of field and the resolving power, the optimum focus position may differ for each channel (for each wavelength component). Therefore, in this case, for example, it is difficult to collectively show the morphological features existing at each depth position (each layer of the fundus) by the MC fundus image taken at one focus position. Further, in recent years, in the technical field of the fundus photography device, a device for photographing the fundus with a wider angle of view has attracted attention. Since the fundus is curved, it becomes more difficult to focus on the entire shooting range as the angle of view of the shooting range increases.

On the other hand, the present device 1 generates a pan-focused (large depth of field) MC fundus image by the image processor 80. An MC fundus image is generated by going through at least three steps of <acquisition step>, <monochromatic composition step>, and <color composition step>. Hereinafter, details will be described with reference to FIGS. 2 to 4.

"First Example"
First, a method of generating an MC fundus image according to the embodiment will be described based on the first embodiment shown in FIG.

<Acquisition step>
As shown in FIG. 2, in the acquisition step, the apparatus 1 acquires a plurality of fundus images captured at different focus positions for one imaging range for each of the plurality of channels showing different primary color components. To do.

In the first embodiment, a plurality of fundus images taken at different focus positions are acquired in each of the three channels R (red), G (green), and B (blue).

The term "acquisition" as used herein means that the fundus image is placed in a state in which it can be processed by the image processor 80. For example, the fundus image is acquired by storing the fundus image in a predetermined memory area accessible by the image processor 80.

A plurality of fundus images taken at different focus positions are taken, for example, in the present device 1 as follows.

That is, while the focus position is changed (moved) by the drive control of the focus adjusting unit 13, the fundus image of each channel is captured for each focus position. For example, a fundus image may be taken each time the focus position is changed by a predetermined diopter. It is desirable that the movement range of the focus position at this time is set so as to include the optimum focus position in each channel.

For example, the moving range of the focus position when a plurality of fundus images are taken may be set based on the focus position immediately after the diopter correction is performed. The diopter of the eye to be inspected is corrected by adjusting the focus position to the position where the contrast is highest in all or a part of the observed image based on the contrast information of the observed image by IR (infrared) light. May occur. IR (infrared) light reaches deeper than light of each color of R (red), G (green), and B (blue). The optimum focus position in the fundus image by IR (infrared) light is deeper than the optimum focus position in the three channels R (red), G (green), and B (blue). Therefore, with reference to the focus position after diopter correction, the predetermined range (for example, the range of the predetermined diopter) on the shallower layer side than the reference is for each channel of R (red), G (green), and B (blue). It may be set as a movement range of the focus position when taking a fundus image. Of course, the reference can be appropriately determined according to the focus position immediately after the diopter correction for each device, and is not necessarily limited to the above position. Further, it is not always necessary to perform diopter correction based on the observed image. For example, when the present device 1 further includes an optical coherence tomography (OCT), the focus position after diopter correction in the OCT may be set as the above reference.

<Single color composition step>
As shown in FIG. 2, a plurality of fundus images having different focus positions are combined by the compositing process by the image processor 80. The fundus image obtained as a result of the compositing process is called a monochromatic composite image. The compositing process is performed for each channel, and a monochromatic composite image is generated for each channel. In the present embodiment, the composition process generates a fundus image having a larger depth of field than the plurality of fundus images acquired in the acquisition step. Such a synthesis process may be, for example, an addition averaging process. As a result of the compositing process, a pan-focused fundus image is obtained for each channel. In this image, the characteristics of the depth position according to the channel (that is, according to the wavelength of the illumination light) are well described. Further, the blur may be removed by deconvolution using the point spread function (PSF).

In the first embodiment, the range of the focus position (this range is also referred to as “composite range”) in the plurality of fundus images on which the monochromatic composite image is based is the same among the respective channels. For example, the monochromatic fundus image of each channel may be generated based on all the fundus images of each channel obtained in the moving range of the focus position at the time of shooting.

<Correction step>
Here, it is conceivable that the eye to be inspected moves while the focus position is changed and a plurality of fundus images are taken. On the other hand, in the compositing process, the image processor 80 may execute in advance a correction process for correcting either the positional deviation between the fundus images or the distortion of the plurality of fundus images.

<Color composition step>
The image processor 80 generates a color composite image based on a plurality of monochromatic composite images obtained for each channel. The color composite image is a multicolor fundus image. The gradation value for each channel of each pixel included in the color composite image is set according to the gradation value of the corresponding pixel in the monochromatic composite image of each channel.

The features of the fundus that are well described in the monochromatic composite image of each channel are also depicted in the color composite image. Therefore, the morphological features existing at each depth position (layer) are collectively shown by one color composite image. In the present embodiment, the color composite image is generated based on the three-channel monochromatic composite image of R (red), G (green), and B (blue), and therefore is morphological between the superficial layer of the retina and the deep layer of the retina. It is easy for the examiner to grasp the features from the color composite image.

Further, in the color composite image, for example, artifacts (for example, a bright spot image) caused by scratches and dust on the surface of the objective lens 19 can be easily reduced. The intermediate image plane (coupling plane with the imaging surface of the apparatus) formed near the objective lens 19 is displaced according to the focus position, and the scratches and dust on the surface of the objective lens 19 overlap with the intermediate image plane of the apparatus. At such a focus position, the above-mentioned artifacts are likely to occur. On the other hand, as the intermediate image plane moves away from the surface of the objective lens 19, the above artifacts are less likely to occur. In the present embodiment, even if the influence of the above artifact is included in a part of the fundus image, it is combined with another fundus image whose focus position is different from the part by the composition process in the monochromatic composition step. Therefore, the influence of the artifact is reduced in the monochromatic composite image and the color composite image generated from the monochromatic composite image.

"Second Example"
Next, a second embodiment according to the embodiment will be described with reference to FIG. The content of the <monochromatic composition step> is different from that of the first embodiment in the second embodiment.

In the monochromatic composition step in the second embodiment, the composition range (the range of the focus position in the fundus image to be combined) is different between the channels. For example, as shown in FIG. 3, the synthesis range may be different from each other among the R (red), G (green), and B (blue) channels.

At this time, for example, the synthesis range in each channel may be set with reference to the optimum focus position for each channel. As shown in FIG. 3, the synthesis range in the B (blue) channel is set to the shallower layer side, the synthesis range in the R (red) channel is set to the deeper layer side, and the G (green) channel is set. The synthesis range in may be set at an intermediate position between the B (blue) channel and the R (red) channel. In this case, in the color composite image based on the monochromatic composite image of each channel, the morphological features between the superficial layer of the retina and the deep layer of the retina are more easily described.

It should be noted that, among the fundus images having different focus positions, the image having the highest contrast in a part or all of the images is regarded as an image taken at the optimum focus position, and the composition range is set based on this. Good. For example, the range of plus or minus predetermined diopters with respect to the reference may be set as the synthesis range.

Further, when an image taken at the optimum focus position (that is, a reference of the focus position) is specified, the addition ratio of another image whose focus position is different from that image is the focus position with the reference image. It may be weighted according to the amount of deviation of. For example, when synthesizing by addition averaging, an image with a smaller amount of deviation of the focus position with respect to a reference may be combined (addition averaging) with a larger addition ratio.

Further, for example, the composition range may be predetermined for each channel as an offset value with respect to the focus position immediately after the diopter correction. In this case, the relationship of the synthesis range in each channel may be predetermined.

"Third Example"
Next, a third embodiment according to the embodiment will be described with reference to FIG. In the third embodiment, in the <color composition step>, image processing is performed to emphasize a part of the monochromatic composite images of the plurality of channels as compared with the remaining part. The image processing may be, for example, contrast enhancement processing for a monochromatic composite image of the channel to be emphasized. Further, it may be a "blurring process" for the monochromatic composite image of the remaining channels. The blurring process may be, for example, a filter process using various filters such as a Gaussian filter. Moreover, both may be used together.

In FIG. 4, a color composite image synthesized without emphasizing any of the three color monochromatic composite images of R (red), G (green), and B (blue) and two of the three colors are blurred. , A color composite image in which the remaining one is emphasized is shown. It can be seen from FIG. 4 that the morphological features that can be grasped on the color composite image change depending on which of the three colors is emphasized.

In the color composite image based on the monochromatic composite image subjected to the above image processing, the components of some channels are emphasized as compared with the components of other channels. As a result, the feature at a specific depth position (or a specific layer) is emphasized on the color composite image which is the MC fundus image, and the examiner can easily grasp the feature. Therefore, in the third embodiment, the examiner can satisfactorily confirm the feature at a specific depth position while utilizing the interpretation knowledge of the color fundus image.

Whether or not the above image processing is performed in the present device 1 may be set according to the input from the examiner. Further, the apparatus 1 may be able to set which channel to emphasize according to the input from the examiner.

Although the above description has been given based on the embodiment, the content of the embodiment can be appropriately changed in carrying out the present disclosure.

Further, for example, in the above embodiment, the addition averaging process is exemplified as the synthesis process in the monochromatic composition step. However, it is not always limited to this. Any one of various image processes for obtaining a monochromatic composite image having a larger depth of field than each of the plurality of fundus images acquired by the acquisition step may be applied as the composite process. For example, the synthesis process may be a weighted average process. Further, the compositing process may be depth compositing (focus stacking). Depth synthesis is a particularly meaningful technique when the effect of curvature on the fundus is large. Further, the depth map may be estimated from the in-focus position in each fundus image. The depth map shows the depth of each area in the shooting range.

Further, for example, in the above embodiment, the fundus imaging device captures a plurality of fundus images having different focus positions by repeatedly photographing the fundus while changing the focus position. However, the present invention is not necessarily limited to this, and the fundus photography apparatus may simultaneously capture a plurality of fundus images having different focus positions according to the principle of the light field camera.

Further, for example, in the above embodiment, the fundus photography apparatus acquires a multicolor image based on a plurality of monochromatic composite images having different channels, but the present invention is not necessarily limited to this. For example, the control unit may specify the image taken at the optimum focus position for each channel after the <acquisition step> of the above embodiment. Then, the control unit may synthesize images taken at the optimum focus position in each channel to generate and acquire a multi-color image.

1 Fundus photography device 1b Control unit 10 Irradiation optical system 20 Light receiving optical system 80 Image processor

Claims (7)

By running on the computer's processor
Acquisition step to acquire a plurality of ophthalmic images taken for each of a plurality of channels showing different wavelength components from a plurality of ophthalmic images taken at different focus positions with respect to one imaging range in the eye to be inspected. When,
A monochromatic compositing step of executing a compositing process for each channel to obtain a monochromatic composite image by compositing a plurality of the ophthalmic images having different focus positions.
An ophthalmic image processing program for causing the computer to perform a color compositing step of generating a color compositing image, which is a multicolor ophthalmic image, based on the monochromatic composite image of a plurality of channels. The ophthalmic image processing program according to claim 1, wherein the range of the focus position in the ophthalmic image to be combined is different for each channel among the plurality of ophthalmic images. In the color composition step, further image processing is performed to emphasize a part of the monochromatic composite image of the plurality of channels with respect to the remaining part, and then the color is based on the monochromatic composite image of the plurality of channels. The ophthalmic image processing program according to claim 1 or 2, which generates a composite image. The ophthalmic image processing program according to claim 3, wherein the computer further executes a setting step for setting whether or not to perform the image processing. The ophthalmology according to any one of claims 1 to 4, further performing a correction step for correcting at least one of misalignment and distortion between the plurality of ophthalmic images taken at different focus positions. Image processing program for. Acquisition step to acquire a plurality of ophthalmic images taken at different focus positions with respect to one imaging range in the eye to be inspected, and a plurality of ophthalmic images captured for each of a plurality of channels showing different wavelength components. When,
A monochromatic compositing step of executing a compositing process for each channel to obtain a monochromatic composite image by compositing a plurality of the ophthalmic images having different focus positions.
An ophthalmic image processing method including a color compositing step of generating a color compositing image which is a multicolor ophthalmic image based on the monochromatic composite image of a plurality of channels. An imaging optical system that captures ophthalmic images by irradiating the eye to be inspected with illumination light of multiple wavelengths.
A plurality of ophthalmic images taken at different focus positions with respect to one imaging range in the eye to be inspected, and a plurality of ophthalmic images captured for each of a plurality of channels showing different wavelength components are acquired by imaging. Control means and
With image processing means,
The image processing means
A compositing process for synthesizing a plurality of the ophthalmic images having different focus positions to obtain a monochromatic composite image is executed for each channel.
Further, an ophthalmologic imaging apparatus that generates a color composite image, which is a multicolor ophthalmic image, based on the monochromatic composite image of a plurality of channels.