CN114831592A - Optical imaging device for ophthalmology and imaging system thereof - Google Patents

Abstract

The invention discloses an optical imaging device for ophthalmology and an imaging system thereof, wherein the imaging device comprises: an imaging channel, an illumination channel, a coefficient channel, a branch channel and a control unit; the imaging channel is used for observing the front of eyes of an inspection object; the illumination channel illuminates the fundus of the examination object in order to shoot the fundus; a coefficient channel branched from the imaging channel for fixing a line of sight of the inspection object while fixing a pupil position of the inspection object; a branch channel branching from the coefficient channel for forming a focus coefficient to the fundus of the examination object; the control unit is used for mechanically or electrically controlling the optical and mechanical structures arranged in any one of the image channel, the illumination channel, the coefficient channel and the branch channel. The optical imaging apparatus for ophthalmology of the present invention can fix the line of sight of an inspection object even when switching from an anterior ocular observation mode to a fundus observation mode, so that an error in pupil position caused thereby can be reduced.

Description

Optical imaging device for ophthalmology and imaging system thereof

technical field

The present application relates to an optical imaging device for ophthalmology and an imaging system thereof capable of photographing and visualizing the eyes and fundus.

Background technique

In general, fundus cameras are widely used in ophthalmology to diagnose the state of a patient's eye by photographing the fundus. Before photographing the eye of the inspection object, the fundus camera needs to be set in a relatively accurate position considering the position of the eye to be inspected, and for the non-mydriatic fundus camera, in order to prevent the pupil from constricting while not obstructing the inspection object's field of vision, Using infrared rays that are invisible to the eyes, the working distance of the fundus camera relative to the eyeball of the inspection object is set.

The initial optical alignment of the fundus camera with respect to the eye to be examined starts from the frontal observation, whereby the fundus camera is placed in the center with the pupil of the eye as a reference and the working distance is set. At this point, the pupil axis of the eye needs to be centered with the axis of the camera, and the eye is as relaxed as possible, as if looking at a point light source at infinity.

According to Existing Patent 1 (US7320519), the photographing process of the front of the eye and the fundus is performed using an anterior-ocular observation optical system 11 in the observation channel (optical axis L3). The optical lens unit 11 is composed of a fixation target plate 42 , an imaging splitting prism 43 and lenses 41 and 44 . In addition, an illumination light source 45 for illuminating the fixation optotype is arranged on the side near the fixation optotype 42 . Then, when photographing the fundus of the inspection subject, the unit 11 is separated from the observation channel (optical axis L3).

However, with the prior patent 1, in the process of switching from the anterior-ocular observation mode to the fundus observation mode, the observation optical unit 11 repeatedly moves on the optical axis L3 line. Inaccurate reset, the target position may move. Therefore, when changing from the frontal observation mode to the fundus observation mode in order to photograph the fundus, during the process of changing the fixation target plate 42 (Fixation target plate) to another optotype 18, the inspection object may miss another visual field in the field of view. Mark 18.

In addition, in the observation unit 11, the auxiliary elements 42, 43 make the design of the unit 11 complicated, and the dichroic prism 43 reduces the image quality of the anterior part of the eye as the observation site during the diagnosis process.

According to the existing patent 2 (US8960908), in the fundus photography mode, in order to fix the pupil axis of the eye of the inspection object in a desired direction, the light from the internal fixation lamp unit 32 is passed through a half mirror (Half mirror) )30 light path into the viewing channel. At the same time, in order to quickly change the eye fixation point, the fixation light unit 32 is manufactured in the form of an LED matrix composed of a plurality of LEDs. At this time, the inspection object fixes the sight line to one of the LEDs illuminated by the sight line LED matrix, and the examiner can obtain images of multiple parts of the fundus by switching the LEDs. When photographing the fundus of a device with this structure, one of the most important processes used by the fundus camera optical system for alignment is focusing on the retina. Thus, the operation is conveniently and accurately performed by using the automatic focusing device constructed by the split unit 22 composed of the LED 221, a Prism forsplitting 222 for splitting the light emitted by the LED 221, and A focus index mask 223 is formed. The focal display assembly on the illumination channel in the device is configured such that the coefficients of the mask 223 lie in a plane that is optically conjugated with the fundus surface. The coefficient mask uses an M2 drive motor to temporarily enter the light path of the illumination channel before focusing. If the focusing function of the focusing lens 28 is limited (eg ±15 diopters), it is not sufficient to compensate for severe ametropia. At this time, the correction lens 29 (Diopter correction lens) uses the M4 motor to enter the optical path of the imaging channel of the imaging optical system 105 (Imaging optical system) (positive lens-291 when the patient is severely hyperopic, negative when the patient is severely short-sighted) Lens-292). The dividing unit 22 and the focusing lens 28 arranged in different optical channels must be moved simultaneously. The segmentation unit 22 is moved along the axis of the illumination channel by the M1 drive motor, and the focusing lens 28 is moved along the axis of the imaging channel by the use of the M3 motor. At this time, the specific position of the focusing lens 28 needs to exactly correspond to the determined position of the dividing unit 22 . This requirement can be achieved by setting corresponding sensors. That is, it is realized by a focus lens position sensor S3 (Focus lens position sensor) and a split position sensor S1 (Split position sensor) that drive the focus lens 28 to focus. At the end of the focusing step, before turning on the white light source for shooting, the segmenting unit 22 is disengaged from the illumination channel by the M2 motor, so as not to cast shadows on the fundus.

However, with the prior patent 2, it is required to precisely move the dividing unit 22 and the focusing lens 28 at the same time and inserting or extracting the dividing unit in the illumination channel, and as an additional mechanical element for this, the driving motors M1, M2, M3 and Sensors S1 and S3 are essential. Therefore, the equipment design is complicated, the mechanical focusing steps are cumbersome, and the operation reliability is low.

According to Existing Patent 3 (US8480232), in order to perform the fundus illumination and alignment process for fundus imaging, the fundus device includes light from an Illumination optical system O1 and an Observation/Imaging system O2 aisle. In the O1 channel, there is a light source unit (Light source unit) 11 including an infrared LED 11a and a white LED 11b, so that infrared or white light can realize fundus visualization. At this time, the two light sources can be moved by means of the driving motor M1, so that the LEDs alternately enter and exit the illumination channel O1. In addition, there is a movable Ring slit 12 to provide a desired path for the light of the light source unit 11 when photographing under conditions of a large pupil or a small pupil of the examination subject. In addition, the device comprises an Alignment index projection unit 17 inside the hole of a holed mirror 16 arranged in the O2 channel, said unit consisting of two IR LEDs 17a and two light guides 17b constitute. The end portion of the light guide protrudes out of the mirror hole. Said unit 17 is designed to control the position of the fundus camera relative to the eye during observation of the fundus by tracking the position of the image reflected from the cornea at the output end of the light guide 17b.

However, in the prior art patent 3, a large number of dynamic components are included in order to realize the above-mentioned action, so that the equipment is more complicated and the instability is increased. In addition, in order to determine the exact position of the fundus camera, the unit 17 is provided with a light guide 17b inside the hole of the mirror 16 through which the eye image passes, which complicates the design and adjustment of the device.

Therefore, when such a fundus camera is operated in the frontal observation mode and the fundus observation mode, respectively, or when it is switched from the frontal observation mode to the fundus observation mode and operated, the pupil of the inspection subject needs to be stably fixed, and the captured fundus image needs to be improved. quality.

The information disclosed in this Background section is only for enhancement of understanding of the general background of the invention and should not be taken as an acknowledgement or any form of suggestion that this information forms the prior art already known to a person of ordinary skill in the art.

SUMMARY OF THE INVENTION

The object of the present invention is to provide an optical imaging device for ophthalmology and an imaging system thereof, which can fix the sight of the inspection object even when switching from the eye observation mode to the fundus observation mode, thereby reducing the resulting Error in pupil position.

In order to achieve the above object, the present invention provides an optical imaging device for ophthalmology, including an imaging channel, an illumination channel, a coefficient channel, a branch channel and a control unit; the imaging channel is used to observe the eyes of the inspection object; the illumination channel is used for photographing the fundus. And illuminate the fundus of the inspection object; the coefficient channel branches from the imaging channel, and is used to fix the pupil position of the inspection object while fixing the line of sight of the inspection object; the branch channel branches from the coefficient channel and is used to form the focus coefficient of the fundus of the inspection object; The control unit is used to mechanically or electrically control the optical and mechanical structures disposed on at least any one of the image channel, the illumination channel, the coefficient channel and the branch channel.

In a preferred embodiment, an ophthalmic lens module, an anterior imaging adapter, an imaging aperture, an imaging lens module, a first beam splitter, and an image receiver are arranged in sequence from the front of the inspection object in the imaging channel. The adapter enters and exits the imaging channel through the first driving motor, and the imaging lens module includes an imaging relay lens and a focusing lens which are sequentially arranged from the front of the inspection object.

In a preferred embodiment, the first beam splitter is formed by a regular hexahedron-shaped polarizing prism.

In a preferred embodiment, an illumination light source part and an illumination relay lens are included in the illumination channel: the illumination light source part irradiates light to the fundus of the inspection object, and the illumination light source part includes a light source and an annular diaphragm; The central axis of the same axis is arranged in a ring shape; the ring diaphragm is used to adjust the light emitted from the light source; the illumination relay lens transmits the light emitted from the illumination light source part to the fundus of the inspection object.

In a preferred embodiment, the ring-shaped light source includes a visible light source and a near-infrared light source, and the visible light source and the near-infrared light source are regularly or irregularly arranged.

In a preferred embodiment, the ring-shaped light source is an LED array with dual wavelength ranges.

In a preferred embodiment, the illumination channel includes an illumination light source portion and an illumination relay lens; the illumination light source portion irradiates light to the fundus of the inspection object, and the illumination light source portion includes a fiber bundle, a visible light source and a near-infrared light source; the fiber bundle is annular , which is formed by the combination of the first optical fiber and the second optical fiber; the visible light source and the near-infrared light source are respectively configured as the entrance of the first optical fiber and the entrance of the second optical fiber; the illumination relay lens transmits the light released from the illumination light source part to the fundus of the inspection object .

In a preferred embodiment, the illumination channel includes an illumination light source portion and an illumination relay lens; the illumination light source portion irradiates light to the fundus of the inspection object, and the illumination light source portion includes a first light source, a second light source and an optical separator, wherein, The light splitter makes the light released by the first light source and the second light source released coaxially, the first light source is arranged on the optical axis of the illumination channel based on the optical splitter, and the second light source is arranged perpendicular to the optical axis of the illumination channel; The relay lens is configured to transmit the light emitted from the illumination light source portion to the fundus of the inspection object.

In a preferred embodiment, a second beam splitter, a collimation coefficient unit, a scaling module, and an LED matrix are arranged in sequence in the coefficient channel, and the collimation coefficient unit includes a collimation coefficient light source and a collimation coefficient light guide; The collimation factor light source forms the point light source required to observe the eyes of the inspection object; the collimation factor light guide is used to guide the light generated from the collimation factor light source.

In a preferred embodiment, the second beam splitter is formed in the shape of a regular hexahedron.

In a preferred embodiment, the zooming module includes a first zooming lens arranged in order to locate the pupil position of the inspection object, an alignment unit including an alignment factor light source and an alignment factor plane light guide, and a second zoom lens.

In a preferred embodiment, a focal coefficient projection unit is arranged in the branch channel, and the focal coefficient projection unit includes a focal coefficient beam splitting prism, a focal coefficient mask and a focal coefficient light source arranged in sequence, and the focal coefficient beam splitting prism includes a flat plate portion and a positive The wedge portion and the negative wedge portion; the flat plate portion is provided in the center; the positive wedge portion and the negative wedge portion have the same inclination with respect to the flat plate portion and are formed on both sides.

In a preferred embodiment, the slits of the focal factor mask are arranged perpendicular to the longitudinal direction of the flat plate portion of the focal factor dichroic prism.

To achieve the above objects, the present invention provides an optical imaging device for ophthalmology, comprising a first light source, a second light source, a third light source, a fourth light source, a fifth light source, a sixth light source, a seventh light source, and a control unit The first light source is configured to observe the imaging channel in front of the inspection object; the second light source and the third light source are configured to illuminate the illumination channel of the eye fundus of the inspection object; The coefficient channel branched by the channel; the seventh light source is configured as a branch channel branched from the coefficient channel; the control unit electrically controls the first light source to the seventh light source; wherein, the control unit makes the first light source and the sixth light source The light source is turned on, the third light source, the fourth light source and the fifth light source are turned on in order to locate the eye fundus of the inspection object, the fourth light source, the fifth light source and the seventh light source are turned on in order to focus the eye fundus of the inspection object, and the light source is turned on for photographing the eye fundus of the inspection object. The second light source is turned on.

In a preferred embodiment, the first light source, the third light source, the fifth light source and the seventh light source are near-infrared light sources, and the second light source, the fourth light source and the sixth light source are white light sources.

In order to achieve the above-mentioned other object, the present invention also provides a simple and stable optical imaging system for ophthalmology, which does not require complex optical structures or mechanical structures to focus on the fundus surface for photographing the fundus. The optical imaging system for ophthalmology includes a photographing part and an image generating part; the photographing part is used to photograph the fundus image of the inspection object, and the photographing part includes an imaging channel, an illumination channel, a coefficient channel, a branch channel and a control unit; the imaging channel is used to observe the inspection object Anterior eye; the illumination channel illuminates the fundus of the inspection object in order to photograph the fundus; the coefficient channel branches from the imaging channel and is used to fix the line of sight of the inspection object while fixing the pupil position of the inspection object; the branch channel branches from the coefficient channel to form a pair of The focal coefficient of the eye fundus of the inspection object; the control unit is used to mechanically or electrically control at least one of the image channel, the illumination channel, the coefficient channel and the branch channel; the image generation unit is used to perform image processing on the fundus image captured by the photographing unit to generate Fundus image.

In order to achieve the above-mentioned further object, the present invention further provides an optical imaging device for ophthalmology and an imaging system thereof, which can improve the degree of freedom when assembling the optical structure. The optical imaging system for ophthalmology includes a photographing part and an image generating part; the photographing part is used for photographing a fundus image of an inspection object, and the photographing part comprises a first light source, a second light source, a third light source, a fourth light source, a fifth light source, a sixth light source and a sixth light source. a light source, a seventh light source and a control unit; the first light source is configured to observe the imaging channel in front of the inspection object; the second light source and the third light source are configured to illuminate the fundus of the inspection object as an illumination channel; the fourth light source and the fifth light source , the sixth light source is configured as a coefficient channel branched from the imaging channel; the seventh light source is configured as a branch channel branched from the coefficient channel; the control unit controls the first to seventh light sources electrically; The first light source and the sixth light source are turned on, the third light source, the fourth light source and the fifth light source are turned on in order to locate the fundus of the inspection object, and the fourth light source, the fifth light source and the seventh light source are turned on in order to focus the fundus of the inspection object. The second light source is turned on in order to photograph the eye fundus of the inspection object; the image generating unit performs image processing on the fundus image captured by the photographing unit to generate a fundus image.

The problems of the present application are not limited to the problems mentioned above, and other problems not mentioned can be clearly understood by those of ordinary skill from the following description.

Compared with the prior art, the optical imaging device for ophthalmology and the imaging system thereof of the present invention has the following beneficial effects: it can stably fix the pupil of the inspection object when photographing the fundus, thereby improving the quality of the fundus image. In addition, various optical structures included in the optical imaging device are stably optically combined with each other, with the effect that mode conversion can be easily performed.

The effects of the present application are not limited to the effects mentioned above, and other effects not mentioned can be clearly understood by those of ordinary skill from the following description.

Description of drawings

FIG. 1 is a diagram schematically illustrating an optical imaging apparatus for ophthalmology according to an embodiment of the present invention.

2 is a diagram showing an electronic block diagram of an optical imaging device for ophthalmology according to the present invention.

FIG. 3 is a diagram briefly illustrating an optical imaging apparatus for ophthalmology according to an embodiment of the present invention.

Fig. 4a is a diagram showing a side view of an illumination light source part arranged in an illumination channel according to an embodiment of the present invention, and Fig. 4b is a cross-sectional view of the light source taken along line X-X of Fig. 4a.

Fig. 5a is a diagram showing a side view of an illumination light source part arranged in an illumination channel according to another embodiment of the present invention, and Fig. 5b is a cross-sectional view of the light source taken along line X-X of Fig. 5a.

6a is a diagram illustrating a side view of an illumination light source part arranged in an illumination channel according to another embodiment of the present invention, and FIG. 6b is a cross-sectional view of the light source module taken along line X-X of FIG. 6a.

FIG. 7 is a schematic diagram illustrating an illumination light source part arranged in an illumination channel according to still another embodiment of the present invention.

FIG. 8 is a diagram for explaining a light transfer process of a collimation coefficient unit according to an embodiment of the present invention.

FIG. 9 is a perspective view illustrating a focal coefficient spectroscopic unit according to an embodiment of the present invention.

10a to 10c are graphs illustrating focal coefficients formed at the image receiver due to the projection of the focal coefficient mask on the fundus according to an embodiment of the present invention.

Description of main reference signs:

100-camera part, 200-drive part, 300-image generation part, 400-control part, 410-mode setting part, 420-lighting switching control part, 430-storage part, 500-operation part, 600-display part, 700 -Optical imaging device for ophthalmology, OI-imaging channel, OL-illumination channel, OX-coefficient channel, OW-branch channel, 71-ophthalmic lens module, 72-anterior imaging adapter, 73-mirror, 74-imaging aperture , 75-imaging lens module, 76-first beam splitter, 77-image receiver, 78-main control unit, Optical axis of OL-OL optical axis, Paseed light ray-transmitting light, Scattered lightrays-scattering light, Mark point-mark point, Vertical axis-center line, central line-vertical axis.

Detailed ways

Embodiments of the present invention will be described in detail below with reference to the accompanying drawings. However, the accompanying drawings are only for revealing the content of the present invention more easily, and those of ordinary skill in the art can easily understand that the scope of the present invention is not limited to the scope of the accompanying drawings.

Also, the terms used in the detailed description of the present invention and the claims are only used to describe specific embodiments, and are not used to limit the present invention. Singular expressions include plural expressions unless the context clearly dictates otherwise.

In the detailed description and claims of the present invention, words such as "comprising", "having" and the like are intended to indicate the presence of the features, quantities, steps, actions, constituent elements, components or combinations thereof described in the specification; it should be understood that this does not The presence or addition of one or more other features, numbers, steps, operations, elements, components or combinations thereof is excluded.

Further, all possible combinations of the embodiments shown in the detailed description of the invention are covered. The various embodiments of the invention, although different from one another, should be understood to be not necessarily mutually exclusive. For example, the specific shapes, structures, and characteristics described herein are associated with one embodiment and may be implemented in other embodiments without departing from the spirit and scope of the present invention. In addition, it should be understood that the positions and arrangements of individual constituent elements within each disclosed embodiment can be changed without departing from the spirit and scope of the present invention. Therefore, the following detailed description is not intended to be limiting, and the scope of the present invention is limited only by all the scope equivalent to the content claimed in the claims and the appended claims, if appropriately described. Like reference numerals in the figures refer to the same or similar functions in various respects.

1 is a diagram briefly illustrating an optical imaging system for ophthalmology according to an embodiment of the present invention, and FIG. 2 is a diagram illustrating an electronic block diagram of the optical imaging system for ophthalmology according to the present invention.

1 and 2 , an optical imaging system 1000 for ophthalmology according to the present invention includes an imaging unit 100 , a driving unit 200 , an image generator 300 , and a controller 400 , an operating unit (Operating unit) 500 and a display unit (Display device) 600 .

As shown in FIG. 1 , the optical imaging system for ophthalmology has a support portion 130 including a base plate 111 and a head support 121 , and obtains a fundus image of an inspection subject supported by the head support 121 . The support portion 130 can be formed in various forms, and can be easily implemented by those skilled in the art, and thus will not be repeated here.

The imaging unit 100 includes an illumination lens module for constituting an illumination optical system, and an imaging lens module for constituting an imaging optical system, such as an ophthalmic lens module, an imaging lens module, and the like. The illumination lens module may include a visible light source and a near/infrared light source with different wavelengths, and may include a light switching unit 110 that selectively switches the visible light source and the near/infrared light source. An infrared light source, so that the light emitted by the visible light source or the near/infrared light source illuminates the fundus of the inspection object. The light source switching unit 110 may be a mechanical unit such as a beam splitter, or may use electronic signal processing to replace the mechanical unit. Such a light source switching unit 110 is controlled by the control unit 400 to selectively operate. The specific structure and operation method of the imaging unit 100 will be described later.

The driving unit 200 is controlled by the control unit 400, and can selectively drive the internal components of the imaging unit 100, such as an illumination lens module or an imaging lens module, according to the selected light source. In addition, the drive part 200 may include a motor drive part for moving the mount.

The image generator 300 is controlled by the control unit 400, performs image processing on the fundus region captured by the imaging unit 100 to generate a fundus image and outputs it, and stores the fundus image in the storage unit 430 or displays it on a display Section 600.

An operating unit 500 includes a mode selection device for allowing medical personnel such as ophthalmologists and ophthalmic nurses to select a visible light imaging mode and an infrared light imaging mode according to the present invention, and various operation devices required for lens focusing operations and the like , and outputs the signal (command) generated by the selection device and the operation device to the control unit 400 .

The operating device may include, but is not limited to, at least one of buttons, joysticks, touch pads, mice, and the like.

The display unit 600 is controlled by the control unit 400 to display operation information generated by the operation of the optical imaging device for ophthalmology of the present invention, and display mode information according to an embodiment of the present invention, and proximity information according to the mode. /At least one of infrared fundus images and visible light fundus images.

The control unit 400 can be a CPU, an AP (Application Processor, application processor), a microcontroller, etc., and includes a mode setting unit (Mode setting unit) 410, a lighting switching control unit (Lightswitching controller) 420, and a storage unit (Memory) 430, The overall operation of the optical imaging device for ophthalmology according to the present invention is controlled.

Specifically, if a mode selection signal is input from the operation section 500 and a mode selection event occurs therefrom, the mode setting section 410 determines which of the eye observation mode, fundus observation mode, and photographing fundus mode, or determines that the mode selection signal is visible light The line imaging mode is also the near/infrared imaging mode, and the drive unit 200 is controlled according to the determined mode, and the internal configuration of the imaging unit 100 is selectively driven.

After the mode setting unit 410 sets the mode, the light switching controller 420 controls the light source switching unit 110 according to the set mode so that visible light or near/infrared light is irradiated to the fundus of the inspection object.

The storage unit (Memory) 430 may include a volatile memory such as RAM (Random Access Memory), a computer-readable medium in the form of a non-volatile memory such as ROM (Read Only Memory) and flash memory, and may include a magnetic disk Drives, for example, include but are not limited to hard disk drives (Hard Disk Drives), solid state drives (Solid State Drives), optical disk drives, and the like. In addition, the storage section 430 includes a program area that stores a control program for controlling the overall operation of the optical imaging apparatus for ophthalmology according to the present invention, and a temporary area that is temporarily stored in the control program generated data; and a data area that stores information input through the operation unit 500 and the image.

FIG. 3 is a diagram briefly illustrating an optical imaging apparatus for ophthalmology according to an embodiment of the present invention.

3 , an optical imaging device 700 for ophthalmology according to the present invention may include various optical and mechanical structures such as an ophthalmic lens module 71, an imaging lens module 75, an illumination relay lens 83, a zoom module 95, a focal coefficient unit 85, and the like The imaging channel OI, the illumination channel OL, the coefficient channel OX, and the branch channel OW can be formed by such an optical structure as a structure that can be inserted into the imaging section 100 of FIG. 1 . In addition, the optical imaging device 700 for ophthalmology may include: a main control unit 78 for mechanically or electrically controlling the optical and mechanical structures; a display part 79 which may An eye or fundus image of the inspection subject presented by the operation of the imaging apparatus 700 is displayed. Additionally, imaging device 700 may include, but is not limited to, electronic devices, controls and displays, mechanical and electrical drives, and the like designed to enable the operation of device components.

The imaging channel (Imaing channel) OI is a channel for visualizing the front of the eye and photographing the fundus through the observation of the eye of the object and the observation of the fundus. In the imaging channel OI, from the fundus (F) of the object to be inspected, an ophthalmic lens module ( Ophthalmic lens module 71, Anterior eye imaging adapter 72, Mirror 73, Imaging aperture 74, Imaging lens module 75, First beam splitter 76 and image Receiver (Imaging camera) 77 .

The ophthalmic lens module 71 may be composed of a plurality of lenses so that the light reflected from the fundus can converge to the position of the mirror 73 and the imaging aperture 74 . An anterior eye illumination light source 71a is disposed adjacent to the ophthalmic lens 71 in the imaging channel OI, and can illuminate the eyes of the inspection subject.

The eye imaging adapter 72 is configured in the imaging channel OI when the inspection object is in the eye observation mode. In the fundus observation mode, the fundus focusing mode or the fundus photographing mode, the first imaging adapter 72 is mechanically or electrically linked with the eye imaging adapter 72. The operation of a drive motor 72a disengages from the imaging channel OI. The first drive motor 72a, under the control of the main control unit 78, can enable the anterior imaging adapter 72 to enter and exit the axis of the imaging channel.

The mirror 73 is an inclined mirror with a hole formed thereon, and is arranged between the ophthalmic lens module 71 and the imaging lens module 75 to reflect the light transmitted through the illumination channel OL in the direction of the fundus of the inspection object. The hole of the mirror 73 The light path may function to converge light reflected from the fundus by means of the ophthalmic lens module 71 and travel toward the imaging lens module 75 . The imaging aperture 74 may be arranged in the same position as the mirror, and adjust the light reflected from the fundus.

The imaging lens module 75 forms a light path channel so that the light passing through the mirror 73 and the imaging aperture 74 is incident on the image receiving part 77, and the imaging lens module 75 may include imaging relay lenses in order from the fundus of the inspection object 75a and a focusing lens 75b. The imaging relay lens 75 may be formed in a module optically combined by a plurality of lenses, and the focusing lens 75b may be mechanically or electrically linked with the second drive motor 75c so as to be movable along the axis of the imaging channel OI.

The first beam splitter 76 separates the incident light amount of the light reflected from the eye or fundus of the inspection subject through the imaging channel OI and transmits it to the image receiver 77 and the coefficient channel OX. In addition, the first beam splitter 76 transmits the incident light through the coefficient channel OX to the front imaging adapter 72 . This first beam splitter 76 can be formed of a cube beam splitter in a regular hexahedron shape, which can eliminate ghosting, improve durability against damage to reflective surfaces, and enhance ease of assembly and adjustment. The beam splitter is formed so as to be able to eliminate light glare that occurs on the surface of the optical lens arranged on the imaging channel OI due to light incident on the coefficient channel OX.

The image receiver 77 is disposed at a predetermined interval from the first beam splitter 76 and includes an image sensor (not shown), and converts the input light into an eye or fundus image signal. At this time, the image sensor may use a CCD (Charge Coupled Device, charge coupled device) image sensor or a CMOS (Complementary Metal Oxide Semiconductor, complementary metal oxide semiconductor) image sensor.

The illumination channel OL is a channel for illuminating the fundus of the inspection target in the fundus observation mode or the fundus photographing mode, and the illumination channel OL may be provided with an illumination channel light source unit 81 for irradiating light to the eye fundus of the inspection target and an illumination light source unit. The light emitted by 81 is transmitted to the illumination relay lens 83 in the direction of the fundus of the inspection object. The illumination light source part 81 may include a visible light source 81a, a near/infrared light source 81b, and a Ring slit 81c for adjusting light emitted from the visible light source 81a and the near/infrared light source 81b. The illumination relay lens 83 can be formed by optically combining a plurality of lenses such as a diffuser lens and a condensing lens as a unit lens module, and the illumination light source unit 81 can be configured in various forms, and specific examples thereof will be described later.

The coefficient channel OX is a channel branched from the imaging channel OI by means of the first beam splitter 76 configured in the imaging channel OI, and is used to fix the pupil position of the inspection object in the eye observation mode, fundus observation mode, and fundus focusing mode At the same time, the sight line of the inspection object is fixed, and the coefficient channel OX can be configured with a second beam splitter (Second beamsplitter) 91, a collimation coefficient unit (Visible index collimating unit) 93, a scaling module (Scaling module) arranged in sequence. ) 95 and the Visible LED matrix 97. In addition, an LED matrix image plane 94 is formed between the collimation coefficient unit 93 and the scaling module 95 , and the LED matrix 97 can be projected on the LED matrix by means of the scaling module 95 Image plane 94.

The second beam splitter 91 directs the light incident through the branch channel OW toward the axial direction of the coefficient channel OX. Such a second beam splitter 91 can be formed of a cube beam splitter in a regular hexahedron shape, which can eliminate ghosting, improve durability against surface damage caused by light reflection, and enhance ease of assembly and adjustment.

The collimation coefficient unit 93 is used to fix the line of sight when visualizing the eyes of the inspection object in the eye observation mode, and may include: a collimating index light source (Collimating index lightsource) 93a, the collimating index light source 93a forms Used to observe the point light source required in front of the inspection object and emit visible light; a collimating index planar light guide 93b, which is used to guide the light source from the collimating index The light released by 93a.

On the other hand, when switching from the frontal observation mode to the fundus observation mode, the frontal imaging adapter 72 arranged in the imaging channel OI is removed from the imaging channel OI, so that the inspection subject loses the target momentarily, and the pupil of the inspection subject for fundus observation There will be errors in position. According to an embodiment of the present invention, even if the eye imaging adapter 72 is removed from the imaging channel OI in the eye viewing mode, the collimation coefficient unit 93 configured in the coefficient channel OX branched from the imaging channel OI keeps the line of sight fixed on the optotype , without causing the inspection object to lose the optotype as the target point, so no errors due to mode changes occur.

The zoom module 95 may include: an alignment unit (Accurate camera alignment unit) 96, the alignment unit (Accurate camera alignment unit) 96 is used for positioning in the fundus observation mode and the fundus focusing mode aiming at the pupil position of the inspection object; first A scaling lens (First scaling lens) 95a and a second scaling lens (Secondscaling lens) 95b are respectively arranged along the axis of the coefficient channel OX into the front and rear of the alignment unit 96 . In addition, the alignment unit 96 includes an alignment index light source (Alignment index light source) 96a emitting near-infrared light and an alignment index light guide (Alignment index planar lightguide) 96b, and operates in a fundus observation mode and a fundus focusing mode.

On the other hand, the collimation coefficient light guide 93b and the alignment coefficient light guide 96b can be made in the form of light guides whose cross section is a four-sided plane, so that they can be arranged away from the optical axis of the coefficient channel 0X.

The LED matrix 97 fixes the eye position of the inspection object in the fundus observation mode, and changes the fixed line-of-sight direction of the inspection object together with the zoom module 95 to observe various parts of the fundus.

The branch channel OW is a channel branched from the coefficient channel OX and used to form a focus coefficient on the fundus of the inspection target in the fundus focusing mode, and may be configured with a focus index light source 85a and a focus index splitting unit (Focus index splitting unit). unit) 85b of the focus index projection unit (Focus index projection unit) 85. The focal coefficient spectroscopic unit 85b can be configured in various forms, which will be described in detail later.

The focal coefficient projection unit 85 is located in an optically conjugated plane with the image plane of the imaging channel OI, and the focusing lens 75b arranged in the imaging channel OI focuses the coefficient image on the fundus, while focusing the coefficient image on the fundus surface. Optically coupled to the plane of the image receiver 77 . Therefore, in a state where the focusing coefficient is fixed, when focusing on the fundus, only the focusing lens 75b in the imaging channel OI operates to capture a fundus image.

The focal coefficient projection unit 85 is configured as a branch channel OW branched from the coefficient channel OX, so that it is not mechanically and mechanically separated from the optical path of the imaging channel OI or the coefficient channel OX when photographing the fundus. Therefore, the optical imaging device 700 according to the present invention does not need to set or move complex optical structures or mechanical and instrument structures when photographing the fundus, and can simply and stably photograph high-quality fundus images.

The optical imaging device 700 for ophthalmology according to the present invention can provide diopter correction according to a large correction range (-10 diopters to +10 diopters) of the optical system in the imaging channel OI without using a correction lens, and can Prevents errors caused by eye refraction in the case of a refractive error of the subject's eye.

Fig. 4a is a diagram showing a side view of an illumination light source part arranged in an illumination channel according to an embodiment of the present invention, and Fig. 4b is a cross-sectional view of the light source taken along line X-X of Fig. 4a.

As shown in FIGS. 4 a and 4 b , the illumination light source unit 81 includes the light sources 41 and 43 and the annular diaphragm 45 arranged at a predetermined interval from the light sources 41 and 43 . The light sources 41 and 43 may include a visible light source 41 and a near-infrared light source 43, have a central axis that coincides with an optical axis (Optical axis) of the illumination channel OL, and are arranged in a ring shape. The light sources 41 and 43 can use, but are not limited to, white LEDs and infrared LEDs. The visible light sources 41 and the near-infrared light sources 43 of the ring light sources 41 and 43 may be alternately arranged regularly or irregularly. The numbers of the visible light sources 41 and the near-infrared light sources 43 can be variously adjusted according to the amount of light required for the fundus observation mode or the fundus photographing mode.

Fig. 5a is a diagram showing a side view of an illumination light source part arranged in an illumination channel according to another embodiment of the present invention, and Fig. 5b is a cross-sectional view of the light source taken along line X-X of Fig. 5a.

As shown in FIGS. 5 a and 5 b , the illumination light source unit 81 may include the light source 51 and the annular diaphragm 55 arranged at a predetermined interval from the light source 51 . As shown in FIG. 4b, the light source 51 may have a central axis that coincides with the optical axis (Optical axis) of the illumination channel OL and be configured in a ring shape. The light source 51 is a dual-band LED capable of irradiating light in both the visible light band and the infrared band, and may include, for example, an LED array ranged with double wavelength.

6a is a diagram illustrating a side view of an illumination light source part arranged in an illumination channel according to another embodiment of the present invention, and FIG. 6b is a cross-sectional view of the light source module taken along line X-X of FIG. 6a.

As shown in FIGS. 6 a and 6 b , the illumination light source part 81 may include a light source module 60 and an annular diaphragm 69 spaced from the light source module 60 by a predetermined interval. The light source module 60 may include a first optical fiber 61a, a second optical fiber 63b, a first condenser lens 62a, a second condenser lens 62b, a visible light source 63a, and a near-infrared light source 61b.

The first optical fiber 61 a and the second optical fiber 63 b are coupled to each other at predetermined positions away from the inlet side to form an annular optical fiber bundle 61 , and the annular optical fiber bundle 61 is fixed by the housing 65 . The visible light source 63a and the near-infrared light source 61b are arranged opposite to each other as the entrance of the first optical fiber 61a and the entrance of the second optical fiber 63b, and the first condenser lens 62a and the second condenser lens 62b are respectively arranged as the visible light source 63a and the first optical fiber. The light emitted from the visible light source 63a and the near-infrared light source 61b is condensed and transmitted to the first optical fiber 61a and the second optical fiber 63b, respectively, between the entrances of 61a and the near-infrared light source 63b and the entrance of the second optical fiber 63b.

The visible light source 63a and the near-infrared light source 61b of the light source module 60 can be arranged in line with the optical axis of the illumination channel OL, and can be arranged and assembled at any position away from the optical axis, thereby improving the degree of freedom of assembly.

FIG. 7 is a schematic diagram illustrating an illumination light source part arranged in an illumination channel according to still another embodiment of the present invention.

As shown in the figure, the illumination light source unit 81 includes a light source 71 , a light separation unit 72 , a condenser lens 73 and an annular diaphragm 75 . The light source 71 includes a visible light source 71 a and a near-infrared light source 71 b arranged in a direction perpendicular to each other with respect to the light separation unit 72 . The visible light source 71a may be a narrow-band visible light source or a narrow-band single-wavelength laser or a visible light emitting diode having a continuum of 400-700 nm that emits narrow-band visible light in the range of 400 nm to 700 nm. The near-infrared light source 71b may be a light-emitting diode having an emission center wavelength in the near-infrared band or a narrow-band single-wavelength laser. Preferably, the near-infrared light emitting diode has a center wavelength of, for example, 740 nm, 760 nm, 800 nm, 810 nm, 850 nm, or 940 nm, and a beam width of, for example, 10 nm to 50 nm, but the present invention is not limited to the above, and has various environments and conditions for realizing the present invention. Various light-emitting diodes of center wavelengths can be used as the near-infrared light source 71b.

The light splitting part 72 may be formed with a non-polarized light splitter such as a beam splitter, so that the near-infrared rays emitted by the near-infrared light source 71b and the visible light emitted by the visible-ray light source 71a can pass through the same illumination channel OL optical axis ( Optical axia) transmission, that is, coaxially transmission. For example, when the near-infrared light source 71b is arranged perpendicular to the optical axis of the illumination channel OL, and the visible light source 71a is arranged on the axis of the illumination channel OL, the non-polarized beamsplitter reflects the light from the near-infrared light source 71b. The emitted near-infrared rays transmit visible light emitted from the visible light source 71a. On the contrary, with the non-polarizing beam splitter as the reference, the near-infrared light source 71b is arranged on the optical axis of the illumination channel OL, and when the visible light source 71a is arranged perpendicular to the optical axis of the illumination channel, the non-polarizing beam splitter makes the near-infrared light source The near-infrared rays emitted by 71b are transmitted and the visible light emitted by the visible light source 41a is reflected.

As described above, the illumination light source unit 81 arranged in the illumination channel according to an embodiment of the present invention can reduce the necessity of mechanical movement of the light source during the transition from fundus illumination using near infrared rays to fundus illumination using visible light, Therefore, the optical imaging device 700 according to the present invention can operate stably.

FIG. 8 is a diagram for explaining a light transfer process of a collimation coefficient unit according to an embodiment of the present invention.

As shown in the figure, the collimation factor unit 93 forms a point light source by a collimation factor light guide 93b and a collimation factor light source 93a composed of a transparent material such as a glass plate. The cross section of the collimation coefficient light guide 93b is a four-sided plane, and light is incident from the collimation coefficient light source 93a arranged on the side surface thereof, and is totally reflected and propagated inside. Most of the light is propagated based on the total reflection condition, but if it encounters a small circular open spot where the total reflection condition is destroyed, the propagated light will be in the form of scattered light rays at that spot (Mark point) freed. This light is recognized by the inspection object as if it were radiating from a point light source against a dark background. Therefore, the collimation coefficient unit 93 fixes the line of sight of the inspection subject when viewing the front of the eye.

On the other hand, the light transfer by the alignment unit 96 is also realized in the same way as the light transfer by the collimation coefficient unit shown in FIG. 8 to align the pupil position of the inspection object.

9 is a perspective view illustrating a focal coefficient spectroscopic unit according to an embodiment of the present invention, and FIGS. 10a to 10c are diagrams illustrating a focal point formed at an image receiver due to a focal coefficient mask projected on the fundus according to an embodiment of the present invention Graph of coefficients.

As shown in FIG. 9 , the focus index splitting unit 85 b included in the focus index projection unit 85 may include a focus index splitting prism 15 and a focus index mask 25 .

The focal coefficient dichroic prism 15 has a disk shape and is divided into three regions, with a flat plate portion 15b in the center, and a positive wedge portion 15a and a negative wedge portion 15c having the same inclination on both sides of the flat plate portion. The focal coefficient mask 25 is optically combined with the focal coefficient dichroic prism 15, has a corresponding circular plate shape, and has a slit 25a formed in the center. The slit 25a of the focal factor mask may be arranged perpendicular to the longitudinal direction of the focal factor dichroic prism flat plate portion 15b.

If the focal factor mask 25 optically combined with the focal factor dichroic prism 15 is projected on the fundus of the inspection subject by the focal factor light source 85a, as shown in Figs. Three focal coefficients 15a1, 15b1, 15c1 corresponding to the three divided parts 15a, 15b, 15c of the focal coefficient dichroic prism 15 are formed in the filter 77. The relative positions of the focal coefficients differ depending on the degree and sign of the fundus defocus.

For example, Fig. 10a shows the case where the central line connecting the centers of the three focal coefficients 15a1, 15b1, and 15c1 is rotated counterclockwise with the vertical axis as the center. The focal point F, the focal point is located in front of the fundus. Fig. 10b shows the case where the line (Centralline) connecting the centers of the three focal coefficients 15a1, 15b1, 15c1 is rotated clockwise with the vertical axis (Vertical axis) as the center, which means that the focus F is more accurately focused on the fundus surface than the , the focus is on the back of the fundus. Fig. 10c shows the case where the central line connecting the centers of the three focal coefficients 15a1, 15b1, and 15c1 coincides with the vertical axis, which means that the focal point is located at the focal point F that is accurately focused on the fundus surface.

When the focal point is to be located on the fundus surface using the focal coefficients in this way, the main control unit 78 analyzes the displayed focal coefficients 15a1, 15b1, 15c1 and generates a defocusing signal, and the generated defocusing signal controls the second drive motor 75c , so that the line connecting the centers of the focus coefficients 15a1, 15b1, and 15c1 coincides with the vertical axis.

Table 1 below is an example in which light sources configured in multiple channels of an optical imaging device according to an embodiment of the present invention operate in multiple modes.

Table 1

As shown in Table 1, when the optical imaging apparatus 700 according to the present invention starts to examine the target eye, it switches to the anterior viewing mode in order to visualize the anterior eye of the eye. The working distance of the apparatus is set in the eye observation mode so that the camera serving as the image receiver 77 is arranged at the center of the pupil with reference to the pupil center axis of the inspection object. Setting may be performed by moving the mobile head of the device relative to the base plate 111 to be fixed using an operating device such as a joystick. In the eye observation mode, the eye illumination light source (first light source) 71a that emits near-infrared light is turned-on, and the eye imaging adapter 72 is inserted into the imaging channel OL through the first drive motor 72a. At this time, the collimation coefficient light source (sixth light source) 93a arranged in the coefficient channel OX as a point light source is turned-on so as to fix the line of sight of the inspection object. Under the control of the main control unit 78 , the frontal image of the inspection object captured by the image receiver 77 is displayed on the display unit 79 . In addition, the frontal image may be stored in memory under the control of the main control unit 78 . On the other hand, if the image in front of the eye captured by the image receiver 77 is out of focus and the pupil is not located in the center of the screen of the display part, then under the control of the main control unit 78, an operating device such as a joystick can be used to set an accurate working distance, in order to be able to obtain the sharpest image of the pupil. In order to easily perform such setting, targets in the form of concentric circles may be displayed on the screen of the display unit under the control of the main control unit 78 . The minimum diameter of the concentric circular target from its center can be set to the size of the smallest pupil viewed from the working distance, and in the picture, the same block along the pupil edge area is displayed in a form that is easy to read the calculated shading index. Therefore, the most accurate pupil focus position can be selected by the examiner.

After the center of the concentric circle target displayed on the screen is aligned with the center of the pupil, the anterior imaging adapter 72 moves out of the imaging channel OL through the first drive motor 72a and simultaneously changes to the fundus observation mode. In the fundus observation mode, the eye illumination light source (first light source) 71a and the collimation coefficient light source (sixth light source) 93a as a visible light source are turned off (turn-off), and at the same time, the illumination channel near-infrared light source (third light source) 81b , the alignment coefficient light source (fifth light source) 96a as near-infrared light and the LED matrix (fourth light source) 97 as visible light are turned-on. The LED matrix 97 functions to move the line of sight of the inspection object by turning on LEDs corresponding to other parts of the eye fundus in the LED matrix 97 so that a plurality of parts can be observed in the fundus of the inspection object.

Then, in the fundus focusing mode, the illumination channel near-infrared light source (third light source) 81b is turned-off, and the focal coefficient light source (seventh light source) 85a serving as near-infrared light is turned-on.

If the operation of the light source installed in the device is appropriately controlled by the method described above at the time of mode switching, the pupil position of the test subject can be accurately fixed and the line of sight can be maintained before fundus photography, and an image can be accurately formed on the fundus surface of the test subject focus.

On the other hand, if the image focus is not formed on the fundus surface, the autofocus system including the focus coefficient projection unit 85, the image receiver 77 and the control unit 78 is activated as described above. The autofocus system analyzes and calculates the focus coefficient formed at the image receiver 77, and controls the second drive motor 75c under the control of the control unit 78 to move the focus lens along the axis of the imaging channel OI. That is, as described above, in order to accurately focus the image on the fundus surface, the control unit 78 may control the second drive motor 75c so that the line passing through the centers of the three focal coefficients coincides with the vertical axis.

As described above, the illumination channel visible light source (second light source) 81a is turned-on after all conditions required for fundus photography are satisfied through the eye observation mode, fundus observation mode, and fundus focusing mode. During the period when the visible light source 81a of the illumination channel is turned on, the image receiver 77 under the control of the control unit 78 captures the fundus image, performs digital image processing and analysis, and stores it in the memory.

Such an optical imaging apparatus 700 according to the present invention can generate an anterior eye image or a fundus image capable of confirming the eye disease of the inspection object through the aforementioned steps, and can repeatedly perform the above steps to generate binocular images of the inspection object.

Embodiments according to the present invention have been examined as described above, but in addition to the above-described embodiments, the present invention may be embodied in other specific forms without departing from the spirit or scope of the invention, as will be appreciated by those of ordinary skill in the art metaphorically. Therefore, the above-described embodiments should be considered as illustrative rather than restrictive, and therefore, the present invention is not limited to the above-described description, but may be modified within the scope of the appended claims and their equivalents.

Claims (17)

1. An optical imaging apparatus for ophthalmology, comprising:

an imaging channel for observing the anterior of an examination subject;

an illumination channel that illuminates the examination-target fundus to photograph the fundus;

a coefficient channel branched from the imaging channel for fixing a line of sight of the inspection object while fixing a pupil position of the inspection object;

a branch channel, which branches from the coefficient channel, for forming a focus coefficient to the fundus of the inspection object; and

a control unit for mechanically or electrically controlling the optical and mechanical structures arranged on at least any one of the image channel, the illumination channel, the coefficient channel, and the branch channel.

2. The optical imaging device for ophthalmology of claim 1, wherein an ophthalmic lens module, an anterior ocular imaging adapter, an imaging aperture, an imaging lens module, a first beam splitter, and an image receiver are arranged in the imaging channel in this order from the anterior of the eye of the inspection object, the anterior ocular imaging adapter enters and exits the imaging channel by a first drive motor, and the imaging lens module includes an imaging relay lens and a focusing lens arranged in this order from the anterior of the eye of the inspection object.

3. The optical imaging device for ophthalmology of claim 2, wherein the first beam splitter is formed by a polarizing prism of a regular hexahedral shape.

4. The optical imaging device for ophthalmology of claim 1, comprising, in the illumination channel:

an illumination light source unit that irradiates light to the fundus oculi of the examination object, the illumination light source unit including:

a light source having a central axis coincident with an optical axis of the illumination channel and arranged in a ring shape; and

an annular diaphragm for modulating light released from the light source; and

and an illumination relay lens that transmits the light emitted from the illumination light source unit to the fundus oculi to be inspected.

5. The optical imaging device for ophthalmology of claim 4, wherein the light source configured in a ring shape comprises a visible light source and a near infrared light source, the visible light source and the near infrared light source being regularly or irregularly arranged.

6. The optical imaging device for ophthalmology of claim 4, wherein the light source configured in a ring is an LED array having a dual wavelength range.

7. The optical imaging device for ophthalmology of claim 1, comprising, in the illumination channel:

an illumination light source unit that irradiates light to the fundus oculi of the examination subject, the illumination light source unit including:

the optical fiber bundle is annular and is formed by combining a first optical fiber and a second optical fiber; and

a visible light source and a near infrared light source configured to be an entrance of the first optical fiber and an entrance of the second optical fiber, respectively; and

an illumination relay lens that transmits the light emitted from the illumination light source section to the examination-target fundus.

8. The optical imaging device for ophthalmology of claim 1, comprising, in the illumination channel:

an illumination light source unit that irradiates light to the fundus oculi of the examination subject with light, the illumination light source unit including a first light source, a second light source, and a light separator that coaxially discharges light discharged from the first light source and the second light source, the first light source being disposed on an optical axis of the illumination tunnel with reference to the light separator, and the second light source being disposed perpendicular to the optical axis of the illumination tunnel; and

an illumination relay lens that transmits the light emitted from the illumination light source section to the examination-target fundus.

9. The optical imaging device for ophthalmology of claim 1, wherein a second beam splitter, a collimation coefficient unit, a scaling module, and an LED matrix are arranged in the coefficient channel in sequence, and the collimation coefficient unit comprises:

a collimation coefficient light source forming a point light source required for observing the front of the eye of the inspection object; and

a collimation factor light guide for guiding light generated from the collimation factor light source.

10. The optical imaging device for ophthalmology of claim 9, wherein the second beam splitter is formed in a regular hexahedron shape.

11. The optical imaging apparatus for ophthalmology of claim 9, wherein the zoom module comprises a first zoom lens, an alignment unit comprising an alignment factor light source and an alignment factor plane light guide, a second zoom lens, which are arranged in sequence for positioning a pupil position of the inspection object.

12. The optical imaging device for ophthalmology according to claim 1, wherein a focus coefficient projection unit is disposed in the branch passage, the focus coefficient projection unit including a focus coefficient beam splitter prism, a focus coefficient mask, and a focus coefficient light source disposed in this order, the focus coefficient beam splitter prism including: a flat plate portion provided at the center; and

a positive wedge portion and a negative wedge portion having the same inclination with respect to the flat plate portion and formed at both sides.

13. An ophthalmic optical imaging device as claimed in claim 12, wherein the aperture of the focus coefficient mask is disposed perpendicularly to a length direction of the flat plate portion of the focus coefficient beam splitter prism.

14. An optical imaging apparatus for ophthalmology, comprising:

a first light source configured to observe an imaging channel in front of an eye of an examination object;

a second light source and a third light source which are configured as an illumination channel for illuminating the fundus of the inspection object;

a fourth light source, a fifth light source, a sixth light source configured as a coefficient channel branching from the imaging channel;

a seventh light source configured as a branch channel that branches from the coefficient channel; and

a control unit that electrically controls the first to seventh light sources;

wherein the control unit turns on the first light source and the sixth light source to observe the anterior ocular segment of the examination object, turns on the third light source, the fourth light source, and the fifth light source to position the ocular fundus of the examination object, turns on the fourth light source, the fifth light source, and the seventh light source to focus on the ocular fundus of the examination object, and turns on the second light source to photograph the ocular fundus of the examination object.

15. The optical imaging device for ophthalmology of claim 14, wherein the first, third, fifth and seventh light sources are near infrared light sources and the second, fourth and sixth light sources are white light sources.

16. An optical imaging system for ophthalmology, comprising:

an imaging unit configured to image a fundus image of an examination target, the imaging unit including:

an imaging channel for observing the anterior of an eye of an examination subject;

an illumination channel that illuminates the examination-target fundus to photograph the fundus;

a coefficient channel branched from the imaging channel for fixing a line of sight of the inspection object while fixing a pupil position of the inspection object;

a branch channel, branched from the coefficient channel, for forming a focus coefficient to the fundus of the examination object; and

a control unit for mechanically or electrically controlling at least one of the image channel, the illumination channel, the coefficient channel, and the branch channel; and

and an image generating unit configured to generate a fundus image by performing image processing on the fundus image captured by the imaging unit.

17. An optical imaging system for ophthalmology, comprising:

an imaging unit configured to image a fundus image of an examination target, the imaging unit including:

a first light source configured to observe an imaging channel in front of an eye of an examination object;

a second light source and a third light source which are configured as an illumination channel for illuminating the fundus of the inspection object;

a fourth light source, a fifth light source, a sixth light source configured as a coefficient channel branching from the imaging channel;

a seventh light source configured as a branch channel that branches from the coefficient channel; and

a control unit electrically controlling the first to seventh light sources;

wherein the first light source and the sixth light source are turned on to observe the anterior ocular segment of the examination subject, the third light source, the fourth light source, and the fifth light source are turned on to position the ocular fundus of the examination subject, the fourth light source, the fifth light source, and the seventh light source are turned on to focus the ocular fundus of the examination subject, and the second light source is turned on to photograph the ocular fundus of the examination subject;

and an image generating unit configured to generate a fundus image by performing image processing on the fundus image captured by the imaging unit.

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