Patent ID: 12207873

DETAILED DESCRIPTION

Representative, non-limiting examples of the present disclosure will now be described in further detail with reference to the attached drawings. This detailed description is merely intended to teach a person of skill in the art further details for practicing preferred aspects of the present teachings and is not intended to limit the scope of the present disclosure. Furthermore, each of the additional features and teachings disclosed below may be utilized separately or in conjunction with other features and teachings to provide improved optical coherence tomographic devices, as well as methods for using and manufacturing the same.

Moreover, combinations of features and steps disclosed in the following detailed description may not be necessary to practice the present disclosure in the broadest sense, and are instead taught merely to particularly describe representative examples of the present disclosure. Furthermore, various features of the above-described and below-described representative examples, as well as the various independent and dependent claims, may be combined in ways that are not specifically and explicitly enumerated in order to provide additional useful embodiments of the present teachings.

All features disclosed in the description and/or the claims are intended to be disclosed separately and independently from each other for the purpose of original written disclosure, as well as for the purpose of restricting the claimed subject matter, independent of the compositions of the features in the embodiments and/or the claims. In addition, all value ranges or indications of groups of entities are intended to disclose every possible intermediate value or intermediate entity for the purpose of original written disclosure, as well as for the purpose of restricting the claimed subject matter.

Some of the features characteristic to below-described embodiments will herein be listed. It should be noted that the respective technical elements are independent of one another, and are useful solely or in combinations. The combinations thereof are not limited to those described in the claims as originally filed.

A first optical coherence tomographic device disclosed herein may comprise: an image capturing unit configured to capture a tomographic image of a subject eye; an input device configured to input one or a plurality of examination report types, each of the examination report types indicating a desired an intended examination result report form; a memory configured to store a plurality of control programs, each of the plurality of control programs, for corresponding one of the examination report types, is used for causing the image capturing unit to perform capturing for generating an examination report of the corresponding type; and a controller configured to control the image capturing unit, when the plurality of examination report types is inputted, according to a series of control programs generated based on corresponding ones of control programs stored in the memory.

In the above-described optical coherence tomographic device, when the plurality of examination report types is inputted, the series of control programs is generated based on the control programs corresponding to the plurality of examination report types that are inputted. Since the image capturing unit is controlled according to the series of control programs, the capturing is performed at once by the series of control programs even when examination reports of the plurality of examination report types are to be generated. Therefore, it is unnecessary to separately perform operations for capturing as many times as the number of examination report types to be generated, and burden on an examinee and burden on an examiner can be reduced.

In the optical coherence tomographic device disclosed herein, the examination report type may comprise a first examination report type indicating a first examination report form and a second examination report type indicating a second examination report form. A first control program corresponding to the first examination report type may include a specific capturing step. A second control program corresponding to the second examination report type may include the specific capturing step. When the first examination report type and the second examination report type are inputted by the input device, the controller may be configured to generate the series of control programs by omitting the specific capturing step comprised in one of the first control program and the second control program. According to such a configuration, when the first examination report and the second examination report are to be generated, it is possible to omit performing the specific capturing step included (overlapping) in both the first examination report and the second examination report. Therefore, a time required for capturing to generate the first examination report and the second examination report can be reduced, and burden on the examinee can be reduced.

In the optical coherence tomographic device disclosed herein, for each of the examination report types, the controller may be configured to generate an examination report of the examination report type based on captured data captured by performing a capturing step corresponding to the examination report type among a group of captured data obtained by performing the series of control programs. According to such a configuration, the examination report is generated by using the captured data appropriate for corresponding one of the examination report types among the group of captured data obtained by performing the series of control programs. For example, the group of captured data obtained by performing the series of control programs may include captured data unnecessary for generating a certain examination report as well as captured data necessary for generating the examination report. By using the captured data appropriate for each of the examination report types, the corresponding examination report can be appropriately generated.

The optical coherence tomographic device disclosed herein may further comprise an output device configured to output examination reports of the plurality of examination report types generated from captured data captured according to the series of control programs. According to such a configuration, the examiner can obtain the examination reports of the plurality of examination report types and grasp results of the examination.

A second coherence tomographic device disclosed herein may comprise: an image capturing unit configured to capture a tomographic image of a subject eye; a memory configured to store a control program for causing the image capturing unit to perform capturing from which examination reports of a plurality of examination report types are able to be generated; a controller configured to cause the image capturing unit to perform the capturing according to the control program stored in the memory; an input device configured to input at least one type of the plurality of examination report types; and a generator configured to generate at least one of the examination reports corresponding to the at least one type inputted by the input device based on specific capturing data comprised in a group of captured data obtained by the controller causing the image capturing unit to perform the capturing according to the control program.

In the above optical coherence tomographic device, the controller is configured to cause the image capturing unit to perform the capturing according to the control program for causing the image capturing unit to execute one capturing from which the examination reports of the plurality of examination report types are able to be generated. Therefore, whichever examination report type(s) is selected among the plurality of examination report types, the generator can generate corresponding one(s) of the examination reports of the plurality of examination report types. For example, even if it is determined that different examination report(s) is necessary after specific examination report(s) is checked, it is unnecessary to perform capturing for generating the different examination report(s). Therefore, it is unnecessary to repeat capturing operations many times, and burden on the examinee and burden on the examiner can be reduced.

EMBODIMENTS

First Embodiment

Hereinafter, an optical coherence tomographic device according to the present embodiment will be described. The optical coherence tomographic device according to the present embodiment is a polarization-sensitive OCT (PS-OCT) that is capable of capturing polarization characteristics of a subject to be examined by a Fourier domain method of a wavelength sweeping type using a light source of a wavelength sweeping type (swept-source optical coherence tomography: SS-OCT).

As illustrated inFIG.1, the optical coherence tomographic device according to the present embodiment comprises a light source11; a measurement optical system (21to29,31,32) that generates a measurement light from light outputted from the light source11; a reference optical system (41to46,51) that generates reference light from the light outputted from the light source11; interference optical systems60,70that combine reflected light from a subject eye500generated in the measurement optical system with the reference light generated in the reference optical system to generate interference light; and interference light detectors80,90that detect the interference light generated in the interference optical system60,70.

(Light Source)

The light source11is a light source of a wavelength sweeping type, and the wavelength (wavenumber) of output light varies with a predetermined cycle. Since the wavelength of light with which the subject eye500is irradiated varies (sweeps), an intensity distribution of light reflected from depthwise portions of the subject eye500can be obtained by subjecting a signal obtained from interference light, which is a combination of the reflected light from the subject eye500and the reference light, to Fourier analysis.

A polarization control device12and a fiber coupler13are connected to the light source11, and a PMFC (polarization maintaining fiber coupler)14and a sampling trigger/clock generator100are connected to the fiber coupler13. Therefore, the light outputted from the light source11is inputted to the PMFC14and the sampling trigger/clock generator100through the polarization control device12and the fiber coupler13. The sampling trigger/clock generator100generates a sampling trigger and a sampling clock for each of signal processors83and93(which will be described later) by using the light from the light source11.

(Measurement Optical System)

The measurement optical system (21to29,31,32) comprises a PMFC21connected to the PMFC14; two measurement light paths S1and S2branching off from the PMFC21; a polarization beam combiner/splitter25connecting the two measurement light paths S1and S2; a collimator lens26connected to the polarization beam combiner/splitter25; galvanometer mirrors27and28; and a lens29. An optical path length difference generator22and a circulator23are disposed on the measurement light path S1. Only a circulator24is disposed on the measurement light path S2. Therefore, an optical path length difference ΔL between the measurement light path S1and the measurement light path S2is generated by the optical path length difference generator22. The optical path length difference ΔL may be set to be longer than a depthwise measurement range of the subject eye500. This prevents interference light with different optical path lengths from overlapping each other. As the optical path length difference generator22, for example, an optical fiber may be used or an optical system such as a mirror, a prism, etc. may be used. In the present embodiment, a PM fiber with a length of one meter is used as the optical path length difference generator22. The measurement optical system further comprises PMFCs31,32. The PMFC31is connected to the circulator23. The PMFC32is connected to the circulator24.

One of light (i.e., measurement light) split by the PMFC14is inputted to the measurement optical system (21to29,31,32). The PMFC21splits the measurement light inputted from the PMFC14into first measurement light and second measurement light. The first measurement light split by the PMFC21is guided to the measurement light path S1, and the second measurement light split by the PMFC21is guided to the measurement light path S2. The first measurement light guided to the measurement light path S1is inputted to the polarization beam combiner/splitter25through the optical path length difference generator22and the circulator23. The second measurement light guided to the measurement light path S2is inputted to the polarization beam combiner/splitter25through the circulator24. A PM fiber304is connected to the polarization beam combiner/splitter25such that the PM fiber304is circumferentially turned by 90 degrees relative to a PM fiber302. For this reason, the second measurement light inputted to the polarization beam combiner/splitter25has a polarization component orthogonal to the first measurement light. Since the optical path length difference generator22is disposed on the measurement light path S1, the first measurement light is delayed relative to the second measurement light by a distance corresponding to the optical path length difference generator22(that is, the optical path length difference ΔL is generated). The polarization beam combiner/splitter25superimposes the inputted first measurement light and second measurement light. The light outputted from the polarization beam combiner/splitter25(superimposed light of the first measurement light and the second measurement light) passes through the collimator lens26, the galvanometer mirrors27and28, and the lens29and is then inputted to the subject eye500. The light inputted to the subject eye500is scanned along an x-y direction by the galvanometer minors27and28.

The light inputted to the subject eye500is reflected by the subject eye500. The reflected light by the subject eye500scatters at the surface of the subject eye500and the inside thereof. The reflected light from the subject eye500passes through, in the reverse order to the incidence path, the lens29, the galvanometer mirrors28,27, and the collimator lens26, and is then inputted to the polarization beam combiner/splitter25. The polarization beam combiner/splitter25splits the inputted reflected light into two polarization components that are orthogonal to each other. These are termed horizontal polarization reflected light (horizontal polarization component) and vertical polarization reflected light (vertical polarization component), for convenience sake. The horizontal polarization reflected light is guided to the measurement light path S1, and the vertical polarization reflected light is guided to the measurement light path S2.

The optical path of the horizontal polarization reflected light is changed by the circulator23, and the horizontal polarization reflected light is inputted to the PMFC31. The PMFC31splits the inputted horizontal polarization reflected light so that it is inputted to each of PMFCs61,71. Therefore, the horizontal polarization reflected light inputted to each of the PMFCs61,71contains a reflected light component based on the first measurement light and a reflected light component based on the second measurement light. The optical path of the vertical polarization reflected light is changed by the circulator24, and the vertical polarization reflected light is inputted to the PMFC32. The PMFC32splits the inputted vertical polarization reflected light so that it is inputted to each of PMFCs62,72. Therefore, the vertical polarization reflected light inputted to each of the PMFCs62,72contains a reflected light component based on the first measurement light and a reflected light component based on the second measurement light.

(Reference Optical System)

The reference optical system (41to46,51) comprises a circulator41connected to the PMFC14; a reference delay line (42,43) connected to the circulator41; a PMFC44connected to the circulator41; two reference light paths R1and R2branching off from the PMFC44; a PMFC46connected to the reference light path R1; and a PMFC51connected to the reference light path R2. An optical path length difference generator45is disposed on the reference light path R1. No optical path length difference generator is disposed on the reference light path R2. Therefore, an optical path length difference ΔL′ between the reference light path R1and the reference light path R2is generated by the optical path length difference generator45. For example, an optical fiber is used as the optical path length difference generator45. The optical path length difference ΔL′ of the optical path length difference generator45may be the same as the optical path length difference ΔL of the optical path length difference generator22. If the optical path length differences ΔL and ΔL′ are the same, depthwise positions of a plurality of interference light (described later) in the subject eye500coincide with each other. That is, it is unnecessary to align a plurality of acquired tomographic images.

The other of light split by the PMFC14(i.e., reference light) is inputted to the reference optical system (41to46,51). The reference light inputted from the PMFC14is inputted to the reference delay line (42,43) through the circulator41. The reference delay line (42,43) includes a collimator lens42and a reference mirror43. The reference light inputted to the reference delay line (42,43) is inputted to the reference mirror43through the collimator lens42. The reference light reflected by the reference mirror43is inputted to the circulator41through the collimator lens42. The reference mirror43is movable in directions to approach and separate from the collimator lens42. In the present embodiment, the position of the reference mirror43is adjusted before the start of measurement so that a signal from the subject eye500will be within an OCT depthwise measurable range.

The optical path of the reference light reflected by the reference mirror43is changed by the circulator41, and the reference light reflected by the reference mirror43is inputted to the PMFC44. The PMFC44splits the inputted reference light into first reference light and second reference light. The first reference light is guided to the reference light path R1, and the second reference light is guided to the reference light path R2. The first reference light is inputted to the PMFC46through the optical path length difference generator45. The reference light inputted to the PMFC46is split into first split reference light and second split reference light. The first split reference light is inputted to the PMFC61through a collimator lens47and a lens48. The second split reference light is inputted to the PMFC62through a collimator lens49and a lens50. The second reference light is inputted to the PMFC51and then is split into third split reference light and fourth split reference light. The third split reference light is inputted to the PMFC71through a collimator lens52and a lens53. The fourth split reference light is inputted to the PMFC72through a collimator lens54and a lens55.

(Interference Optical System)

The interference optical systems60,70include a first interference optical system60and a second interference optical system70. The first interference optical system60includes the PMFCs61and62. As described, the horizontal polarization reflected light from the measurement optical system and the first split reference light (light having the optical path length difference ΔL′) from the reference optical system are inputted to the PMFC61. Here, the horizontal polarization reflected light contains a reflected light component (light having the optical path length difference ΔL) based on the first measurement light and a reflected light component (light that does not have the optical path length difference ΔL) based on the second measurement light. Therefore, in the PMFC61, the first split reference light is combined with the reflected light component (light having the optical path length difference ΔL) based on the first measurement light which is among the horizontal polarization reflected light, as a result of which first interference light (horizontal polarization component) is generated.

The vertical polarization reflected light from the measurement optical system and the second split reference light (light having the optical path length difference ΔL′) from the reference optical system are inputted to the PMFC62. Here, the vertical polarization reflected light contains a reflected light component (light having the optical path length difference ΔL) based on the first measurement light and a reflected light component (light that does not have the optical path length difference ΔL) based on the second measurement light. Therefore, in the PMFC62, the second split reference light is combined with the reflected light component (light having the optical path length difference ΔL) based on the first measurement light which is among the vertical polarization reflected light, as a result of which second interference light (vertical polarization component) is generated.

The second interference optical system70includes the PMFCs71and72. As described, the horizontal polarization reflected light from the measurement optical system and the third split reference light (light that does not have the optical path length difference ΔL′) from the reference optical system are inputted to the PMFC71. Therefore, in the PMFC71, the third split reference light is combined with a reflected light component (light that does not have the optical path length difference ΔL) based on the second measurement light which is among the horizontal polarization reflected light, as a result of which third interference light (horizontal polarization component) is generated.

The vertical polarization reflected light from the measurement optical system and the fourth split reference light (light that does not have the optical path length difference ΔL′) from the reference optical system are inputted to the PMFC72. Therefore, in the PMFC72, the fourth split reference light is combined with the reflected light component (light that does not have the optical path length difference ΔL) based on the second measurement light which is among the vertical polarization reflected light, as a result of which fourth interference light (vertical polarization component) is generated. The first interference light and the second interference light correspond to the measurement light that has passed through the measurement light path S1, and the third interference light and the fourth interference light correspond to the measurement light that has passed through the measurement light path S2.

(Interference Light Detectors)

The interference light detectors80,90include a first interference light detector80configured to detect the interference light (the first interference light and the second interference light) generated in the first interference light generator60, and a second interference light detector90configured to detect the interference light (the third interference light and the fourth interference light) generated in the second interference light generator70.

The first interference light detector80comprises balanced light detectors81and82(which may simply be termed detectors81,82hereinbelow), and a signal processor83connected to the detectors81and82. The PMFC61is connected to the detector81, and the signal processor83is connected to an output terminal of the detector81. The PMFC61splits the first interference light into two interference light that have phases different from each other by 180 degrees, and inputs the two interference light to the detector81. The detector81performs differential amplification processing and noise reduction processing to the two interference light having phases different from each other by 180 degrees inputted from the PMFC61so as to convert them to an electric signal (first interference signal), and outputs the first interference signal to the signal processor83. That is, the first interference signal is an interference signal HH between the reference light and the horizontal polarization reflected light from the subject eye500based on the horizontal polarization measurement light. Similarly, the PMFC62is connected to the detector82, and the signal processor83is connected to an output terminal of the detector82. The PMFC62splits the second interference light into two interference light that have phases different from each other by 180 degrees, and inputs the two interference light to the detector82. The detector82performs differential amplification processing and noise reduction processing to the two interference light having phases different from each other by 180 degrees so as to convert them to an electric signal (second interference signal), and outputs the second interference signal to the signal processor83. That is, the second interference signal is an interference signal HV between the reference light and the vertical polarization reflected light from the subject eye500based on the horizontal polarization measurement light.

The signal processor83comprises a first signal processing unit84to which the first interference signal is inputted, and a second signal processing unit85to which the second interference signal is inputted. The first signal processing unit84is configured to sample the first interference signal based on a sampling trigger and a sampling clock inputted to the signal processor83from the sampling trigger/clock generator100. The second signal processing unit85is configured to sample the second interference signal based on the sampling trigger and the sampling clock inputted to the signal processor83from the sampling trigger/clock generator100. The first and second interference signals sampled in the first signal processing unit84and the second signal processing unit85are inputted to a processor202(which will be described later). A known data acquisition device (a so-called DAQ) may be used as the signal processor83.

Similar to the first interference light detector80, the second interference light detector90comprises balanced light detectors91and92(which may simply be termed detectors91,92hereinbelow), and the signal processor93connected to the detectors91and92. The PMFC71is connected to the detector91, and the signal processor93is connected to an output terminal of the detector91. The PMFC71splits the third interference light into two interference light that have phases different from each other by 180 degrees, and inputs the two interference light to the detector91. The detector91performs differential amplification processing and noise reduction processing to the two interference light having phases different from each other by 180 degrees so as to convert them to an electric signal (third interference signal), and outputs the third interference signal to the signal processor93. That is, the third interference signal is an interference signal VH between the reference light and the horizontal polarization reflected light from the subject eye500based on the vertical polarization measurement light. Similarly, the PMFC72is connected to the detector92, and the signal processor93is connected to an output terminal of the detector92. The PMFC72splits the fourth interference light into two interference light that have phases different from each other by 180 degrees, and inputs the two interference light to the detector92. The detector92performs differential amplification processing and noise reduction processing to the two interference light having phases different from each other by 180 degrees so as to convert them to an electric signal (fourth interference signal), and outputs the fourth interference signal to the signal processor93. That is, the fourth interference signal is an interference signal VV between the reference light and the vertical polarization reflected light from the subject eye500based on the vertical polarization measurement light.

The signal processor93comprises a third signal processing unit94to which the third interference signal is inputted, and a fourth signal processing unit95to which the fourth interference signal is inputted. The third signal processing unit94is configured to sample the third interference signal based on a sampling trigger and a sampling clock inputted to the signal processor93from the sampling trigger/clock generator100. The fourth signal processing unit95is configured to sample the fourth interference signal based on the sampling trigger and the sampling clock inputted to the signal processor93from the sampling trigger/clock generator100. The third and fourth interference signals sampled in the third signal processing unit94and the fourth signal processing unit95are inputted to the processor202(which will be described later). A known data acquisition device (a so-called DAQ) may also be used as the signal processor93. According to the above configuration, it is possible to acquire the interference signals indicative of four polarization characteristics of the subject eye500. In the present embodiment, the signal processors83,93, each of which comprises two signal processing units, are used, however, different configurations may be employed. For example, one signal processor comprising four signal processing units may be used, or four signal processors each comprising one signal processing unit may be used.

Next, the configuration of a control system of the optical coherence tomographic device according to the present embodiment will be described. As illustrated inFIG.2, the optical coherence tomographic device is controlled by a calculation unit200. The calculation unit200comprises the processor202, the first interference light detector80, and the second interference light detector90. The first interference light detector80, the second interference light detector90, and the processor202are connected to a measurement unit10. The processor202is configured to output a control signal to the measurement unit10to move an incidence position of the measurement light to the subject eye500by driving the galvanometer mirrors27and28. The first interference light detector80acquires first sampling data with respect to the interference signals (the interference signal HH and the interference signal HV) inputted from the measurement unit10based on a sampling clock1inputted from the measurement unit10and by using a sampling trigger1as a trigger, and outputs the first sampling data to the processor202. The processor202performs calculation processing such as Fourier transform, etc. to the first sampling data to generate an HH tomographic image and an HV tomographic image. The second interference light detector90acquires second sampling data with respect to the interference signals (the interference signal VH and the interference signal VV) inputted from the measurement unit10based on a sampling clock2inputted from the measurement unit10and by using a sampling trigger2as a trigger, and outputs the second sampling data to the processor202. The processor202performs calculation processing such as Fourier transform, etc. to the second sampling data to generate a VH tomographic image and a VV tomographic image. The HH tomographic image, the VH tomographic image, the HV tomographic image, and the VV tomographic image are tomographic images at the same position. Thus, the processor202can create tomographic images with four polarization characteristics (HH, HV, VH, VV) that represent a Jones matrix of the subject eye500.

The processor202includes a memory204. The memory204stores a plurality of control programs, each of which is for generating an examination report indicating a result of an examination on the subject eye500in a specific examination report form and a plurality of control programs, each of which is for performing capturing in accordance with an examination report type corresponding to the examination report. Each of the control programs for generating the examination reports is stored in the memory204for corresponding one of the examination report types. Each of the control programs for performing capturing is stored in the memory204in association with the corresponding one of the examination report types for the corresponding one of the examination report types. Each of the control programs for performing capturing is constituted by one or more capturing steps, and the capturing step(s) necessary for generating the examination report corresponding to the control program is set in advance. More specifically, the memory204stores an examination report name and corresponding one of the control programs for preforming capturing in association with each other. These control programs may be set by the examiner. That is, the examiner may set specific capturing condition(s) for each of the capturing step(s) constituting corresponding one of the control programs, and associate the condition(s) with the corresponding examination report name to set the same as the control program. The control program set by the examiner can also be stored in the memory204. Specific examples of the examination reports and the control programs for performing capturing including the capturing step(s) associated with examination reports will be described later.

As illustrated inFIG.3, the sampling trigger/clock generator100comprises a fiber coupler102, a sampling trigger generator (140,142,144,146,148,150,152), and a sampling clock generator (160,162,164,166,168,170,172,174). The light from the light source11is inputted, through the fiber coupler13and the fiber coupler102, to each of the sampling trigger generator140and the sampling clock generator160.

(Sampling Trigger Generator)

The sampling trigger generator140may generate a sampling trigger by using, for example, an FBG (fiber bragg grating)144. As illustrated inFIG.3, the FBG144reflects only a component of the light inputted from the light source11that has a specific wavelength, thereby generating a sampling trigger. The generated sampling trigger is inputted to a distributor150. The distributor150distributes the sampling trigger into the sampling trigger1and the sampling trigger2. The sampling trigger1is inputted, through a signal delay circuit152, to the processor202. The sampling trigger2is directly inputted to the processor202. The sampling trigger1is a trigger signal for the interference signals (the first interference signal and the second interference signal) inputted from the first interference light detector80to the processor202. The sampling trigger2is a trigger signal for the interference signals (the third interference signal and the fourth interference signal) inputted from the second interference light detector90to the processor202. The signal delay circuit152is designed such that the sampling trigger1is delayed relative to the sampling trigger2by a time corresponding to the optical path length difference ΔL of the optical path length difference generator22. This makes it possible to make a frequency at which the sampling of the interference signals inputted from the first interference light detector80is started equal to a frequency at which the sampling of the interference signals inputted from the second interference light detector90is started. Only the sampling trigger1may be generated. Since the optical path length difference ΔL is known, the sampling of the interference signals inputted from the second interference light detector90may be started such that the start time is delayed from the sampling trigger1by a time corresponding to the optical path length difference ΔL.

(Sampling Clock Generator)

The sampling clock generator may be configured of a Mach-Zehnder interferometer, for example. As illustrated inFIG.3, the sampling clock generator generates a sampling clock with the same frequency by using the Mach-Zehnder interferometer. The sampling clock generated by the Mach-Zehnder interferometer is inputted to a distributor172. The distributor172distributes the sampling clock into the sampling clock1and the sampling clock2. The sampling clock1is inputted, through a signal delay circuit174, to the first interference light detector80. The sampling clock2is directly inputted to the second interference light detector90. The signal delay circuit174is designed to cause a delay by a time corresponding to the optical path length difference ΔL of the optical path length difference generator22. This makes it possible to sample interference light with the delay corresponding to the optical path length difference generator22at the same timing Thus, positional misalignment among a plurality of acquired tomographic images can be prevented. In the present embodiment, a Mach-Zehnder interferometer is used to generate the sampling clocks. Alternatively, a Michelson interferometer or an electric circuit may be used to generate the sampling clocks. Alternatively, the sampling clocks may be generated by using a light source including a sampling clock generator.

Next, with reference toFIG.4, a process to generate examination report(s) of the subject eye500will be described. As illustrated inFIG.4, first, the processor202displays examination report types that can be generated by the optical coherence tomographic device of the present embodiment on the monitor120(seeFIG.2) (S12). The memory204stores the examination report types that can be generated by the optical coherence tomographic device of the present embodiment. The processor202causes the monitor120to display all the examination report types that can be generated and are stored in the memory204.

For example, in the present embodiment, it is assumed that four examination reports of “Polarization Map”, “Macula Map”, “Glaucoma Map” and “Optic Disc Shape Analysis” can be generated. In this case, as illustrated inFIG.5, the processor202causes the monitor120to display the four examination report types of the “Polarization Map”, “Macula Map”, “Glaucoma Map” and “Optic Disc Shape Analysis” in a selectable manner.

Next, the processor202determines whether one or a plurality of examination report types have been selected (S14). Specifically, the examiner selects one or a plurality of examination reports types each corresponding to an intended examination from the plurality of examination report types displayed on the monitor120by using an input means (not shown) such as a mouse. In the example illustrated inFIG.5, the examiner selects one or a plurality of intended examination report types from the “Polarization Map”, “Macula Map”, “Glaucoma Map” and “Optic Disc Shape Analysis”. Here, the number of examination report type(s) selected by the examiner is not particularly limited. Therefore, the examiner can select a plurality of intended examination report types. For example, the examiner selects three examination report types: the “Polarization Map”, “Macula Map”, and “Glaucoma Map”. When an operation of selecting the one or plurality of examination report types is completed, the examiner instructs completion of the selection operation. For example, the examiner instructs the completion of the selection operation by pressing an “OK” button displayed on the monitor120using the input means. The processor202awaits until the completion of the selection operation is instructed (NO in step S14).

When the completion of the selection operation is instructed (YES in step S14), the processor202identifies capturing step(s) associated with each of the examination report types selected in step S14(S16). As described above, the memory204stores the capturing step(s) necessary for generating each of the one or plurality of examination reports in association with the corresponding examination report type. The processor202reads out, from the memory204, the capturing step(s) corresponding to each the one or plurality of examination report types selected in step S14.

For example, as illustrated inFIG.6, the memory204stores a plurality of examination report types, corresponding capturing step(s) for each of the examination report types and detailed capturing conditions of the capturing step(s). In the example illustrated inFIG.6, the capturing step of “Polarization Map” is “Cube”. Accordingly, the processor202determines that the capturing step of the selected “Polarization Map” is “Cube.” Similarly, the processor202determines that the capturing step of the selected “Macula Map” is “Cube”, and determines that the capturing steps of the selected “Glaucoma Map” are “Cube” and “Cube Disk”.

Next, in step S18, the processor202determines whether there is overlapping capturing step(s) among the capturing step(s) identified in step S16. When a plurality of examination report types is selected in step S14, there may be a case where capturing step(s) associated with the selected examination report types overlap one another (that is, the same capturing step(s) is included in the selected examination report types). For example, as illustrated inFIG.6, when the “Polarization Map”, “Macula Map” and “Glaucoma Map” are selected, the capturing step of “Cube” overlaps in all three examination report types. Therefore, when the three examination report types of the “Polarization Map”, “Macula Map” and “Glaucoma Map” are selected in step S14, the processor202determines that the capturing step of “Cube” overlaps.

When there is overlapping capturing step(s) (YES in step S18), the processor202deletes the overlapping capturing step(s) (S20). For example, if three examination report types of the “Polarization Map”, “Macula Map” and “Glaucoma Map” are selected in step S14, the capturing steps identified in step S16are the “Cube” associated with the “Polarization Map”, the “Cube” associated with the “Macula Map”, and the “Cube” and “Cube Disk” associated with the “Glaucoma Map”. Therefore, the list of all the capturing steps associated with the three selected examination report types is the “Cube”, “Cube”, “Cube” and “Cube Disk”, thus there are three “Cube”. In this instance, the processor202deletes the overlapping “Cube” (i.e., two of the three “Cube”) from the listed four capturing steps. Then, the two capturing steps of “Cube” and “Cube Disk” are left. On the other hand, when there is no overlapping capturing step (NO in step S18), the processor202skips step S20.

Next, the processor202generates a series of control programs (hereinafter, also referred to as a capturing program) based on the capturing step(s) identified in Steps S16to S20(S22). If it is determined in step S18that there is overlapping capturing step(s), the overlapping capturing step(s) is deleted in step S20. Therefore, the overlapping capturing step(s) is deleted from all the capturing steps identified in step S16, and the capturing program is generated for the remaining capturing step(s). For example, when three examination report types of the “Polarization Map”, “Macula Map” and “Glaucoma Map” are selected in step S14, the two capturing steps of “Cube” and “Cube Disk” are left after step S20. Accordingly, the processor202generates the capturing program to perform the two capturing steps of the “Cube” and “Cube Disk”. On the other hand, when it is determined that there is no overlapping capturing step in step S18, the processor202generates the capturing program so as to execute all the capturing step(s) identified in step S16.

Next, the processor202performs capturing of the subject eye500(S24) in accordance with the capturing program generated in step S22. The process of capturing the subject eye500is performed under the following procedure. First, the examiner manipulates a manipulation member such as a joystick (not shown) to align the optical coherence tomographic device with respect to the subject eye500. That is, the processor202operates a position adjustment mechanism (not shown) in accordance with the examiner's manipulation of the manipulation member. As a result, a position of the optical coherence tomographic device in xy directions (vertical and horizontal directions) and a position of the optical coherence tomographic device in z directions (forward and backward directions) with respect to the subject eye500are adjusted. Thereafter, the processor202performs capturing of the subject eye500according to the capturing program. As described above, the capturing program consists of one or more capturing steps, and detailed setting conditions (capturing conditions) for each of the one or more capturing steps are stored in the memory204. The processor202performs the capturing program in accordance with the detailed setting conditions stored in the memory204. For example, when the three examination report types of the “Polarization Map”, “Macula Map” and “Glaucoma Map” are selected in step S14, a capturing program consisting of the two capturing steps of the “Cube” and “Cube Disk” is generated. Consequently, the processor202performs the two capturing steps of the “Cube” and “Cube Disk” according to the capturing program. Captured data captured in each of the capturing step(s) is stored in the memory204. In the following, a plurality of pieces of data captured in each of the capturing step(s) may be collectively referred to as “a group of captured data”.

When the capturing of the subject eye500is completed, the processor202generates the examination report(s) of the examination report type(s) selected in step S14(S26). In step S24, one or more capturing steps are performed, and the captured data captured in each of the one or more capturing steps is stored in the memory204. The processor202generates each of the examination report(s) by using the captured data captured in the capturing step(s) corresponding to the examination report type(s) from the group of captured data.

For example, when the three examination report types of the “Polarization Map”, “Macula Map” and “Glaucoma Map” are selected in step S14, the two capturing steps of the “Cube” and “Cube Disk” are performed. As illustrated inFIG.6, the capturing step corresponding to the “Polarization Map” is the “Cube”. Consequently, the processor202generates the “Polarization Map” by using the captured data captured in the “Cube”. Since the capturing step corresponding to the “Macula Map” is the “Cube”, the processor202also generates the “Macula Map” by using the captured data captured in the “Cube”. Both the “Polarization Map” and the “Macula Map” can be generated by using the captured data captured in the “Cube”, and each of the “Polarization Map” and the “Macula Map” can be generated by changing the analysis procedures, site(s) to be analyzed of the subject eye500, and the like. In addition, since the captured steps corresponding to the “Glaucoma Map” are the “Cube” and the “Cube Disk”, the captured data captured in the “Cube” is also used for generating the “Glaucoma Map”. As described above, when a plurality of examination report types that can be generated by performing the same capturing step(s) is selected, captured data captured in the same capturing step(s) (in the present embodiment, the “Cube”) can be used to generate any of the different examination reports once the same capturing step(s) is performed. In the present embodiment, when the capturing step(s) overlap, the overlapping capturing step(s) is deleted to generate the capturing program. Consequently, a time required for capturing can be reduced, and burden on an examinee can be reduced.

Even when there is no overlapping capturing step, after one or a plurality of examination report types are selected, the capturing program is generated by combining capturing step(s) so that all the selected examination report(s) can be generated. For example, in the example illustrated inFIG.6, when two examination report types of the “Polarization Map” and “Optic Disc Shape Analysis” are selected, the “Cube” corresponding to the “Polarization Map”, and the “Cube Disk” and the “Circle Disk” corresponding to the “Optic Disc Shape Analysis” are identified as the capturing steps. Consequently, the capturing program consisting of the three steps of the “Cube”, “Cube Disk” and “Circle Disk” is generated. When this capturing program is performed, the three capturing steps of the “Cube”, “Cube Disk” and “Circle Disk” are performed in a series of operations. As such, since capturing for generating a plurality of examination reports is executed at a time, it is not necessary to separately instruct and perform capturing for generating each of the examination reports, and it is possible to reduce a time required for capturing all the examination reports.

Lastly, the processor202displays the examination report(s) generated in step S26on the monitor120(S28). When a plurality of examination report types is selected, all the examination reports may be displayed on a single screen, or each of the examination reports may be displayed such that the examination reports are switched from one to the other to display only one examination report on a single screen.

FIG.7is an example of display images600of the polarization map. The polarization map is generated by analyzing the captured data captured in the capturing step set as “Cube”. As illustrated inFIG.7, the polarization map includes a fundus image602, a tomographic image604, an en-face image606indicating thickness, an en-face image608indicating entropy, and an en-face image610indicating birefringence of the subject eye500. The tomographic image604shows a cross section at a position indicated by the arrow in the fundus image602. Each of the en-face images606,608, and610shows a region surrounded by the square in the fundus image602. The polarization map also includes an en-face image612indicating thickness, an en-face image614indicating entropy, and an en-face image616indicating birefringence of an eye in a normal state (hereinafter, also referred to simply as a “normal eye”) that differs from the subject eye500. Since the polarization map includes the en-face images612,614, and616of the normal eye, the condition of the subject eye500can be easily grasped by comparing the subject eye500with the normal eye. As described above, by virtue of the polarization map including the images relating to various polarizations that can be generated from the captured data captured in the “Cube”, it becomes easier to grasp the state of the subject eye500.

FIG.8is an example of display images700of the macula map. The macula map is generated by analyzing the captured data captured in the capturing step set as the “Cube”. As illustrated inFIG.8, the macula map includes a fundus image702, a tomographic image704, an en-face image706indicating thickness, a tomographic image708indicating entropy, and maps710and712indicating quantitative evaluations of an average value of thickness and volume, respectively, and maps714and716indicating the surface of the subject eye500. Each of the tomographic images704and708shows a cross-section at a position indicated by the arrow in the fundus image702. The en-face e image706indicates an area surrounded by the square in the fundus image702. Each of the maps710,712indicating quantitative evaluations corresponds to circles and lines shown in the en-face images706indicating thickness. The macula map also includes an en-face images718indicating thickness of the normal eye. As described above, by virtue of the macula map including various images relating to the macule which can be generated from the captured data captured in the “Cube”, it becomes easier to grasp the state of the macule of the subject eye500.

FIG.9is an example of display images800of the glaucoma map. The glaucoma map is generated by analyzing two pieces of captured data captured in the capturing steps set as “Cube” and “Cube Disk”. As illustrated inFIG.9, the glaucoma map includes a fundus image802, a tomographic image804, and en-face images806and808indicating thickness of the subject eye500. The tomographic image804shows a cross section at a position indicated by the arrow in the fundus image802. The en-face image806shows a region surrounded by the right square in the fundus image802(a region including the macula), and the en-face image808shows a region surrounded by the left square in the fundus image802(a region including an optic nerve head). The tomographic image804and the en-face image806are generated from the captured data captured in the “Cube”, and the en-face image808is generated from the captured data captured in the “Cube Disk”. The glaucoma map also includes a plurality of en-face images810each indicating thickness of the normal eye. Each of the plurality of en-face images810is an en-face image of the normal eye in various depthwise ranges, and is generated from the captured data obtained by capturing the normal eye in each of the “Cube” and “Cube Disk”. As described above, by virtue of the glaucoma map including the various images relating to glaucoma which can be generated from the captured data captured in the “Cube” and the “Cube Disk”, it becomes easier to grasp the disease state relating to the glaucoma of the subject eye500.

Second Embodiment

In the first embodiment described above, the intended examination report type(s) is selected from the plurality of examination report types, and capturing of the subject eye500is performed so that the examination report(s) of the selected examination report types can be generated, but such a configuration is not limiting. For example, the subject eye500may be captured according to a capturing program capable of generating examination reports of all of the plurality of examination report types that can be selected. The present embodiment is different from the first embodiment in that the memory204is configured to store one capturing program including capturing steps capable of generating all of the examination reports of all the plurality of examination report types, and the rest of its configurations is the same as the first embodiment. Therefore, the description of the same configuration as that of the first embodiment is omitted.

FIG.10is a flowchart illustrating an example of a process of generating examination report(s) of the subject eye500in the present embodiment. As illustrated inFIG.10, the processor202at first performs capturing of the subject eye500in accordance with the capturing program stored in the memory204(S32). In the first embodiment described above, the capturing program is generated in accordance with the selected examination report type(s), and the capturing of the subject eye500is executed in accordance with the generated capturing program. In the present embodiment, however, the capturing of the subject eye500is performed in accordance with the preset capturing program.

For example, in the present embodiment, it is assumed that three examination reports of the “Polarization Map”, “Macula Map” and “Glaucoma Map” can be generated. As described above, the capturing step for generating the “Polarization Map” is “Cube”, the capturing step for generating the “Macula Map” is “Cube”, and the capturing steps for generating the “Glaucoma Map” are “Cube” and “Cube Disk” (seeFIG.6). Therefore, the capturing program capable of generating the three examination reports of “Polarization Map”, “Macula Map” and “Glaucoma Map” is set to include “Cube” and “Cube Disk”. Therefore, the processor202performs the two capturing steps of the “Cube” and “Cube Disk” according to the capturing program. The captured data captured in each of the capturing steps is stored in the memory204.

Next, as illustrated inFIG.10, the processor202causes the monitor120to display the examination report types that can be generated (S34). For example, in the example described above, the three examination reports that can be generated are the “Polarization Map”, “Macula Map” and “Glaucoma Map”. In this case, the processor202displays the three examination report types of the “Polarization Map”, “Macula Map”, and “Glaucoma Map” on the monitor120.

Next, it is determined whether one or a plurality of examination report types have been selected (S36). The process of step S36is the same as the process of step S14of the first embodiment, and therefore a detailed description thereof is omitted.

When the one or plurality of examination report types are selected, the processor202generates the examination report(s) corresponding to the examination report type(s) selected in step S36(S38). At this time, among a group of the captured data stored in the memory204, captured data captured in the capturing step(s) corresponding to the selected examination report type(s) is used. For example, when the “Polarization Map” and “Macula Map” are selected in step S36, the processor202generates the “Polarization Map” and the “Macula Map” using the captured data captured in the “Cube”. Thereafter, the processor202displays the examination report(s) generated in step S38on the monitor120(S40).

In the above-described examples, since the examiner selects the “Polarization Map” and “Macula Map” even though the two capturing steps of “Cube” and “Cube Disk” are performed according to the preset capturing program, only the captured data captured in the “Cube” is used, and the captured data captured in the “Cube Disk” is not used. However, when the examiner intends to generate the “Glaucoma Map” after the capturing, the “Glaucoma Map” can be generated using the captured data captured in the “Cube Disk” among the already captured data. Therefore, while a single capturing time may be longer, examination report(s) that is different from the examination report(s) intended at the time of capturing can be generated without recapturing. There may be a case where other examination report(s) may be needed as a result of evaluation on the examination report(s) intended at the time of capturing. In such a case, other examination report(s) can be generated without recapturing, and burden on an examinee and an examiner can be reduced.

In the above embodiments, the polarization-sensitive optical coherence tomographic device is used, but such a configuration is not limiting. A type of optical interference tomography is not particularly limited, and it may for example be an optical coherence tomographic device that is not polarization-sensitive. Further, in the second embodiment, the examination report type(s) of the examination report(s) to be outputted is selected after the capturing, but the capturing may be started after the examination report type(s) is selected as with the first embodiment.

Specific examples of the disclosure herein have been described in detail, however, these are mere exemplary indications and thus do not limit the scope of the claims. The art described in the claims includes modifications and variations of the specific examples presented above. Technical features described in the description and the drawings may technically be useful alone or in various combinations, and are not limited to the combinations as originally claimed. Further, the purpose of the examples illustrated by the present description or drawings is to satisfy multiple objectives simultaneously, and satisfying any one of those objectives gives technical utility to the present disclosure.