WO2021172505A1 - Appareil d'imagerie ophtalmologique - Google Patents

Appareil d'imagerie ophtalmologique Download PDF

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Publication number
WO2021172505A1
WO2021172505A1 PCT/JP2021/007299 JP2021007299W WO2021172505A1 WO 2021172505 A1 WO2021172505 A1 WO 2021172505A1 JP 2021007299 W JP2021007299 W JP 2021007299W WO 2021172505 A1 WO2021172505 A1 WO 2021172505A1
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Prior art keywords
scanning
light
measurement light
fundus
optical
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PCT/JP2021/007299
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English (en)
Japanese (ja)
Inventor
佳洋 角谷
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興和株式会社
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Priority to JP2022503742A priority Critical patent/JPWO2021172505A1/ja
Publication of WO2021172505A1 publication Critical patent/WO2021172505A1/fr

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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B3/00—Apparatus for testing the eyes; Instruments for examining the eyes
    • A61B3/10—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions

Definitions

  • the present invention relates to an ophthalmologic imaging device for photographing the fundus by projecting light onto the fundus of the eye to be inspected while scanning the measurement light from the light source and receiving the reflected light from the fundus.
  • Patent Document 1 has been proposed.
  • Patent Document 1 is a scanning fundus photography apparatus that scans a laser beam two-dimensionally, projects it onto the fundus, receives reflected light from the fundus, and photographs the fundus, and is an objective composed of a plurality of lenses. There is disclosed a scanning fundus photography apparatus capable of photographing the fundus with high image quality by blocking harmful reflected light rays derived from the lens surface reflection of the lens.
  • the laser light affects the human body, and depending on how it is used, it causes an excessive burden on the eye to be inspected, which is a problem.
  • the present invention has been made in view of the above problems, and an object of the present invention is to provide an ophthalmologic imaging apparatus capable of reducing the burden on the eye to be inspected.
  • the ophthalmologic imaging apparatus includes an optical device unit for scanning the measurement light from the light source, incidenting it on the fundus of the eye to be inspected, and receiving the return light reflected by the fundus, and the light is reflected by the fundus.
  • An ophthalmologic imaging device that captures an image of the fundus of the eye based on the return light, wherein the measurement light is scanned with a predetermined position of the eye to be inspected as a scanning turning point, and the measuring light intermittently scans the scanning turning point. It is characterized by including a control unit that controls the optical device unit so as to pass through.
  • the optical apparatus unit includes a first scanning device that scans the measurement light in the first direction and a second scanning device that scans the measurement light in the second direction.
  • the first scanning device and the control unit so as to execute a raster scan in which scanning in the first direction is repeated a plurality of times while scanning once in a predetermined range predetermined in the second direction. It is characterized by controlling a second scanning device.
  • control unit further has the optical device unit so that the outside of the passable range in which the measurement light can pass and reach the eye to be inspected is also a scanning range. It is characterized in that the measurement light passing through the scanning turning point is made intermittent light.
  • control unit further controls the optical device unit so as to modulate the measurement light output from the light source, and transmits the measurement light passing through the scanning turning point. It is characterized by intermittent light.
  • the modulation is further characterized in that the measurement light is modulated by a direct modulation, an electro-optical modulation, an acoustic-optical modulation, or an optical chopper.
  • FIG. 1 is a block diagram showing an example of a configuration of an ophthalmologic imaging apparatus corresponding to at least one of the embodiments of the present invention.
  • the ophthalmologic imaging device 100 includes an optical device unit 60, a control unit 70, an input device 80, and a display device 90.
  • FIG. 2 is an optical diagram showing an example of the configuration of an optical device unit in an ophthalmologic imaging device corresponding to at least one of the embodiments of the present invention.
  • the optical device unit 60 is roughly divided into a light projecting optical system 1, a scanning optical system 2, an objective lens optical system 3, and a light receiving optical system 4.
  • the configuration of the optical device unit 60 shown in FIG. 2 is an example, and the same functions as those of the light projecting optical system 1, the scanning optical system 2, the objective lens optical system 3, and the light receiving optical system 4 are realized. If possible, the configuration may be different from that shown in FIG.
  • each of the light projecting optical system 1, the scanning optical system 2, the objective lens optical system 3, and the light receiving optical system 4 of the optical device unit 60 of FIG. 1 are controlled by the control unit 70. It is given as an example of a configuration that can be a target, and is only an example. Therefore, there is a possibility that a configuration other than this is a control target.
  • the projection optical system 1 is composed of, for example, a laser light source 10, a projection lens 11, a projection pinhole 12, and a projection focus lens 13.
  • a laser light source 10 a laser light source for each of the three colors R, G, and B for color photographing and a NIR laser (near-infrared laser) for alignment are used.
  • NIR laser near-infrared laser
  • an optical member that superimposes the optical axes of these plurality of light sources on one is required.
  • the laser light from the laser light source 10 passes through the light projecting lens 11 and is incident on the light projecting pin hole 12 arranged at a position conjugate with the fundus conjugate surface, and the diameter of the laser light is narrowed by the light projecting pin hole 12.
  • the projection focus lens 13 is movable along the optical axis direction of the light source unit 10, and adjusts the focus of the laser beam with respect to the fundus 50b of the eye 50 to be inspected.
  • the laser light transmitted through the projection focus lens 13 is incident on the optical path dividing mirror (pupil dividing mirror) 14.
  • the scanning optical system 2 is composed of, for example, a first scanning device 20, scanning relay lenses 21 and 22, and a second scanning device 23.
  • the laser light incident on the optical path dividing mirror 14 is reflected there and is incident on the first scanning device 20.
  • the first scanning device 20 is a device for scanning the laser beam in the first direction.
  • the laser light scanned by the first scanning device 20 is incident on the second scanning device 23 via the scanning relay lenses 21 and 22.
  • the second scanning device 23 is a device for scanning the laser beam in the second direction orthogonal to the first direction.
  • scanning by the first scanning device 20 is performed at a higher speed than scanning by the second scanning device 23.
  • a polygon mirror (rotating multifaceted mirror) may be adopted as the first scanning device 20, and a galvano mirror (vibration mirror) may be adopted as the second scanning device 23. Then, the laser light reflected by the second scanning device 23 is incident on the objective lens optical system 3.
  • the objective lens optical system 3 is composed of a first lens group 30 and a second lens group 31.
  • the laser light scanned by the first scanning device 20 and the second scanning device 23 enters the pupil 50a of the eye 50 to be inspected through the first lens group 30 and the second lens group 31 as measurement light, and is projected onto the fundus 50b. ..
  • the fundus 50b is raster-scanned with laser light.
  • the laser light projected on the fundus 50b is reflected by the fundus 50b, and the reflected light travels in the same optical path in the opposite direction and passes through the objective lens optical system 3.
  • the objective lens optical system 3 is configured such that the fundus conjugate surface 32 exists between the first lens group 30 and the second lens group 31, and the fundus image is formed on the fundus conjugate surface 32. ..
  • the position indicated by reference numeral 50a is the position of the scanning turning point described later.
  • the laser light that has passed through the objective lens optical system 3 is reverse-scanned in the second direction and the first direction by the scanning optical system 2, and becomes a light beam having a light beam thicker than the light ray before being incident on the scanning optical system 2 to divide the optical path. It is incident on the mirror 14. Since the center of the optical path dividing mirror 14 is arranged so as to coincide with the optical axis and the reflected light from the outside of the mirror is passed through the light receiving optical system 4, the optical path is divided into a light projecting light path and a light receiving light path. On the other hand, the optical path on the side to be inspected from the optical path dividing mirror 14 is a common optical path for the light projecting optical system 1 and the light receiving optical system 4.
  • the light-receiving optical system 4 is composed of, for example, a light-receiving focus lens 40, a light-shielding member 41, a light-receiving pinhole 42, a light-receiving lens 43, a condenser lens 44, and a light-receiving element 45.
  • the reflected light from the fundus 50b that has passed through the optical path dividing mirror 14 passes through the light receiving focus lens 40 and the light receiving pin hole 42, passes through the light receiving lens 43 and the condensing lens 44, and is then received by the light receiving element 45.
  • the light receiving element 45 includes a light receiving element that receives a laser light source of each of the three colors R, G, and B for color photographing, and a light receiving element that receives an IR laser for alignment.
  • a light receiving element that receives a laser light source of each of the three colors R, G, and B for color photographing
  • a light receiving element that receives an IR laser for alignment.
  • an optical member that separates the laser light of each color into these plurality of elements is required.
  • the light receiving pinhole 42 is arranged near a position conjugate with the fundus 50b
  • the light shielding member 41 is arranged near a position conjugate with the lens surface of the objective lens optical system 3, which is harmful from the lens surface of the objective lens optical system 3. The reflected light is blocked to avoid the occurrence of a central spot image (false image).
  • the light receiving element 45 is composed of, for example, a photodiode, and sends the luminance information of each point of the fundus 50b that has been raster-scanned to the control unit 70.
  • the control unit 70 constructs a fundus image from the scanning position of the fundus 50b and its brightness information.
  • the diopter adjustment mechanism for adjusting the diopter of the eye 50 to be inspected is provided in the light emitting optical system 1 and the light receiving optical system 4, respectively.
  • the light projecting focus lens 13 of the light projecting optical system 1 and the light receiving focus lens 40 of the light receiving optical system 4 are used as lenses for diopter adjustment, and the light projecting focus lens 13 and the light receiving focus lens 40 are used as light.
  • Diopter adjustment can be performed by moving them in conjunction with each other along the axis.
  • the light-shielding member 41 also moves along the optical axis in conjunction with the light-emitting focus lens 13 and the light-receiving focus lens 40.
  • the control unit 70 includes, for example, a drive control unit 71, an image generation unit 72, and a storage unit 73.
  • the drive control unit 71 has a function of executing control of each unit to be controlled by the optical device unit 60.
  • Examples of the control target of the optical device unit 60 include a laser light source 10, a projection focus lens 13, a first scanning device 20, a second scanning device 23, a light receiving focus lens 40, a light shielding member 41, and a light receiving element 45. Be done.
  • the image generation unit 72 has a function of constructing a fundus image from the information of the received data corresponding to each scanning position of the fundus 50b received by the light receiving element 45.
  • the storage unit 73 has a function of storing various programs for drive control and also storing data of the fundus image generated by the image generation unit 72.
  • the input device 80 has a function of receiving an input operation from the operator of the ophthalmologic imaging device 100.
  • the input device 80 corresponds to, for example, an input device such as a mouse, a keyboard, and a touch panel, as well as operation buttons when configured as a dedicated device.
  • the display device 90 has a function of displaying a fundus image or the like generated by the image generation unit 72.
  • FIG. 7 is an explanatory diagram showing a scanning method in the ophthalmologic imaging apparatus of the comparative example.
  • the range through which the light beam (measurement light) from the light source can pass and reach the eye to be inspected is the "passable range”
  • the range in which the measurement light is scanned by the scanning device is the "scanning range”
  • the range to be photographed is defined as the range to be photographed.
  • the passable range can be set by the lens barrel, the diaphragm, the lens diameter, and the like constituting the optical device unit 60.
  • the photographing range and the scanning range match, and the photographing range and the scanning range are included in the passable range.
  • the high-speed scan for the first scan horizontal direction
  • the low-speed scan for the second direction vertical direction
  • the following problems are concerned.
  • FIG. 3 is an explanatory diagram for explaining the path of the measurement light when the eye to be inspected is observed from the side when taking a picture with the fundus photography device.
  • it is necessary to change the angle of incidence of the measurement light on the eye to be inspected for scanning. Almost always, there is a scanning turning point where the measurement light passes. Therefore, in the method of constantly scanning within the passable range as in the comparative example, the measurement light is continuously irradiated to the scanning turning point. As a result, the burden on the pupil where the scanning turning point is located and the cornea, iris, and crystalline lens around the pupil tends to increase.
  • the first embodiment is characterized in that the measurement light passing through the scanning turning point is made intermittent light by setting the outside of the passable range as the scanning range.
  • FIG. 4 is an explanatory diagram showing an example of a scanning method in an ophthalmologic imaging apparatus corresponding to at least one of the embodiments of the present invention.
  • the scanning method shown in FIG. 4 shows a state of overscan in which the measurement light is also scanned outside the passable range. Assuming that the direction from right to left is the first direction which is the scanning direction of the first scanning device 20, and the direction from top to bottom is the second direction which is the scanning direction of the second scanning device 23, two scans are performed. The directions are orthogonal and the scanning range is rectangular. Further, in the present embodiment, as shown in FIG. 4, a scanning range is set outside the passable range.
  • the measurement light that scans within the passable range (indicated by the solid line) will be incident on the eye to be inspected as in the comparative example, but the measurement light that scans outside the passable range (indicated by the alternate long and short dash line) will be incident on the eye to be inspected.
  • the time of scanning outside the passable range is the non-irradiation time at the scanning turning point because the light is not incident on the scanning turning point.
  • the optical device is designed so that the scanning range of the first scanning device 20 covers a predetermined range outside the scanning relay lens 21 or the first lens group 30 where light does not enter, and / or the second scanning. It is conceivable to design or adjust the optical device so that the scanning range of the device 23 is targeted to a predetermined range outside where light does not enter the first lens group 30.
  • a galvano mirror is adopted as an example of the second scanning device 23, a method of designing an optical device so as to overscan in the second scanning direction and uniformly performing control by the control unit 70 and a control unit.
  • a method of variably controlling the swing angle of the galvano mirror to switch overscan on / off can be considered.
  • the measurement light of the entire scanning range by the first scanning device 20 passes through the scanning relay lens 21, but a part of the measurement light is blocked between the scanning relay lenses 21 and 22 to limit the passable range. Therefore, it is conceivable to set the time for scanning outside the passable range to the non-irradiation time at the scanning turning point. Further, the measurement light of the entire scanning range is passed through to the scanning optical system 2 in the previous stage of the first lens group 30, but a part of the measurement light emitted by the objective lens optical system 3 after the first lens group 30 is emitted.
  • an optical device unit for scanning the measurement light from the light source, incidenting it on the fundus of the eye to be inspected, and receiving the return light reflected by the fundus.
  • This is an ophthalmologic imaging device that captures an image of the fundus of the eye based on the return light reflected by the fundus.
  • the control unit is provided with a control unit that controls the optical device unit so that the light passes through the optical device unit, and the control unit has an optical device unit so that the outside of the passable range that defines the range through which the measurement light can pass and reaches the eye to be inspected is also the scanning range. Since the measurement light passing through the scanning turning point is changed to intermittent light, it is possible to reduce the burden on the eye to be inspected at the time of photographing as compared with the comparative example.
  • the time for scanning within the passable range is compared. If the same scanning time as the shooting is assigned, the time required for the shooting is 1.5 times that of the comparative example. According to this method, even if the total power of the measurement light emitted in the vicinity of the scanning turning point is the same, the irradiation power per unit time with respect to the measurement time can be reduced, so that the eye to be inspected at the time of photographing. The burden on the device can be reduced.
  • the measurement light is treated as a continuous wave, and it is necessary to evaluate it based on the limit value for the continuous wave device in "ISO 15004-2", which is the optical hazard standard for the ocular optical device.
  • the device is treated as a pulse device, which is a standard of an ophthalmic optical device, "ISO”. The evaluation will be based on the limit value for pulse equipment in "15004-2".
  • the standard for the limit value for the pulse device is relaxed rather than the limit value for the continuous wave device, so the method of the first embodiment can reduce the burden on the eye to be inspected. Not only that, it has the advantage of being easy to meet the standards of ophthalmic optical devices for photographing the fundus.
  • the shooting range and the scanning range are the same as in the comparative example, but the measurement light passing through the scanning turning point is transmitted by modulating the measurement light output from the light source. It is characterized by intermittent light.
  • FIG. 5 is an explanatory diagram showing an example of a scanning method in an ophthalmologic imaging apparatus corresponding to at least one of the embodiments of the present invention.
  • the scanning method shown in FIG. 5 represents a state in which the measurement light output from the laser light source 10 is modulated into so-called pulse-shaped intermittent light in which the irradiation period and the non-irradiation period change periodically.
  • the direction of scanning from right to left is the first direction which is the scanning direction of the first scanning device 20
  • the direction of scanning from top to bottom is the second direction which is the scanning direction of the second scanning device 23.
  • the scanning range is rectangular.
  • the scanning range of the second embodiment is within the passable range of the measurement light unlike the first embodiment, but the measurement light modulated in a pulse shape is used. Therefore, the measurement light passing through the scanning turning point is regarded as intermittent light.
  • any means may be used as long as the measurement light can be modulated in a pulse shape.
  • the modulation method for example, in addition to direct modulation that directly controls the current flowing through the laser light source 10, an external modulation method such as an electro-optical modulator (EOM), an acousto-optic modulator (AOM), or an optical chopper can be adopted.
  • EOM electro-optical modulator
  • AOM acousto-optic modulator
  • optical chopper an optical chopper
  • the pulse duration is required to be less than 0.25 seconds, that is, 4 Hz or more, as a condition adopted in "ISO 15004-2", which is an optical hazard standard for ophthalmic optical equipment. Further, it is preferable to determine the balance between the number of samplings and the shooting time.
  • an on period (irradiation period) appears at least once at each point to be sampled, and there is also an off period (non-irradiation period) between adjacent sampling points. Need to appear. That is, it is necessary that one cycle or more elapses at one sampling point. For example, as a shooting condition, when the number of scans is 3000 and 3000 points are sampled per scan, it is necessary to sample a total of 9 million points, and if the shooting time is 0.4 seconds, one time. In order to sample without omission in shooting, it is preferable to modulate the frequency so that the frequency is 22.5 MHz or higher. Further, there may be a method of setting to match the sampling rate of the sampling board (for example, 240 MHz).
  • an optical device unit for scanning the measurement light from the light source, incidenting it on the fundus of the eye to be inspected, and receiving the return light reflected by the fundus.
  • This is an ophthalmologic imaging device that captures an image of the fundus of the eye based on the return light reflected by the fundus.
  • the control unit is provided to control the optical device unit so as to pass through the optical device unit, and the control unit controls the optical device unit so as to modulate the measurement light output from the light source, and intermittently transmits the measurement light passing through the scanning turning point. Since the light is used, it is possible to reduce the burden on the eye to be inspected at the time of photographing as compared with the comparative example.
  • the duty ratio ratio of the irradiation period in one cycle
  • the irradiation time of the measurement light is halved as compared with the case where the modulation is not performed under the same conditions. Therefore, it is possible to reduce the irradiation energy for the scanning turning point and reduce the burden on the eye to be inspected at the time of photographing.
  • FIG. 6 is a table showing a comparison of scanning methods in an ophthalmologic imaging apparatus corresponding to at least one of the embodiments of the present invention.
  • the comparative example shown in FIG. 7 is carried out, the overscan described in the first embodiment is carried out, and the laser modulation described in the second embodiment is carried out. Is compared with.
  • the irradiation power is the same, but the measurement time is 1.5 times, so that per unit time. It is possible to reduce the irradiation power. Under the conditions illustrated as the comparative example of FIG. 6, the irradiation power becomes 127.3 (mW / cm 2 ), which exceeds the limit value of the irradiation power of the continuous wave device of 100 (mW / cm 2 ), which is considered unsuitable. turn into.
  • the irradiation energy per imaging is 6.4 ⁇ 10-2 (J / cm 2 ). Is 1.5 (J / cm 2 ) or less, which is the limit value of the irradiation energy per imaging in the case of the pulse device, and it can be seen that it conforms to the standard of the standard in the case of the pulse device.
  • the laser modulation is irradiated as compared with the comparative example. It is possible to halve the energy.
  • the irradiation energy per imaging is 3.2 ⁇ 10-2 (J / cm 2 ), which is the limit value of the irradiation energy per imaging in the case of the pulse device. It is 1.3 (J / cm 2 ) or less, and it can be seen that it conforms to the standard of the standard in the case of pulse equipment.
  • Ophthalmic imaging device 1
  • Floodlight optical system 2 Scanning optical system 3
  • Objective lens optical system 4 Light receiving optical system 10
  • Laser light source 11
  • Floodlight lens 12
  • Floodlight pinhole 13
  • Floodlight focus lens 14
  • Optical path split mirror 20
  • Horizontal scanning device 21
  • Scanning relay Lens 22 Scanning relay lens 23
  • Vertical scanning device 30
  • 1st lens group 31
  • 2nd lens group 32
  • Fundus conjugate surface 40
  • Light receiving focus lens 41
  • Light shielding member Light receiving pinhole
  • Light receiving lens 44 Condensing lens 45
  • Light receiving element 50 Eye to be inspected 50a Eye ( Position of scanning turning point)
  • Fundus 60
  • Control unit 71
  • Drive control unit 72
  • Image generation unit 72
  • Storage unit 80
  • Input device 90 Display device 90 Display device

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  • Health & Medical Sciences (AREA)
  • Medical Informatics (AREA)
  • Biophysics (AREA)
  • Ophthalmology & Optometry (AREA)
  • Engineering & Computer Science (AREA)
  • Biomedical Technology (AREA)
  • Heart & Thoracic Surgery (AREA)
  • Physics & Mathematics (AREA)
  • Molecular Biology (AREA)
  • Surgery (AREA)
  • Animal Behavior & Ethology (AREA)
  • General Health & Medical Sciences (AREA)
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  • Eye Examination Apparatus (AREA)

Abstract

L'invention concerne un appareil d'imagerie ophtalmologique qui capture une image du fond d'un œil sur la base de la lumière de retour réfléchie par le fond de l'œil, l'appareil comprenant : un ensemble dispositif optique qui, afin de permettre de réduire la contrainte sur un œil à examiner, effectue un balayage avec la lumière de mesure provenant d'une source de lumière, amène la lumière de mesure à entrer dans le fond de l'œil à examiner et reçoit la lumière de retour réfléchie par le fond de l'œil; et une unité de commande qui commande l'ensemble dispositif optique de telle sorte que le balayage avec la lumière de mesure est effectué alors qu'une position prédéterminée de l'œil à examiner sert de point de changement de direction du balayage et la lumière de mesure passe par intermittence à travers le point de changement de direction du balayage.
PCT/JP2021/007299 2020-02-27 2021-02-26 Appareil d'imagerie ophtalmologique WO2021172505A1 (fr)

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Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JPH04244134A (ja) * 1991-01-28 1992-09-01 Sony Corp 眼科装置
JP2012143284A (ja) * 2011-01-07 2012-08-02 Topcon Corp 走査型レーザー検眼装置
JP2016133550A (ja) * 2015-01-16 2016-07-25 キヤノン株式会社 レーザスキャナ装置、レーザスキャン方法、およびプログラム
WO2019172206A1 (fr) * 2018-03-05 2019-09-12 株式会社ニデック Dispositif et programme de traitement d'image de fond d'œil

Patent Citations (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JPH04244134A (ja) * 1991-01-28 1992-09-01 Sony Corp 眼科装置
JP2012143284A (ja) * 2011-01-07 2012-08-02 Topcon Corp 走査型レーザー検眼装置
JP2016133550A (ja) * 2015-01-16 2016-07-25 キヤノン株式会社 レーザスキャナ装置、レーザスキャン方法、およびプログラム
WO2019172206A1 (fr) * 2018-03-05 2019-09-12 株式会社ニデック Dispositif et programme de traitement d'image de fond d'œil

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