JP2020185025A - Ophthalmic laser treatment apparatus - Google Patents

Abstract

To provide an ophthalmic laser treatment apparatus enabling a treatment site to be confirmed in detail.SOLUTION: The ophthalmic laser treatment apparatus for treating a patient's eye comprises: irradiation means irradiating the patient's eye with laser beams for treatment; deflection means for deflecting the laser beams; and narrow region photographing means for photographing a narrow region fundus image of the patient's eye. The irradiation means and the narrow region photographing means share the deflection means. This makes it possible to confirm a treatment site in detail.SELECTED DRAWING: Figure 3

Description

The present disclosure relates to an ophthalmic laser treatment apparatus that treats a patient's eye by irradiating a laser beam.

An ophthalmic laser treatment device for irradiating a patient's eye with a laser beam to treat the patient's eye is known to include a fundus photography unit (see Patent Document 1). In such an ophthalmic laser treatment device, a wide-area fundus image is acquired by a fundus imaging unit, and a laser beam is applied to an arbitrary portion of the wide-area fundus image.

JP-A-2010-148635

However, conventional ophthalmic laser treatment devices have not been suitable for detailed confirmation of treatment sites.

The technical subject of the present disclosure is to provide an ophthalmic laser treatment apparatus capable of confirming a treatment site in detail in view of the problems of the prior art.

In order to solve the above problems, the present disclosure is characterized by having the following configurations.

(1) An ophthalmic laser treatment apparatus for treating a patient's eye, which comprises an irradiation means for irradiating the patient's eye with a therapeutic laser beam, a deflection means for deflecting the laser beam, and the patient's eye. A narrow-range photographing means for capturing a narrow-range fundus image of the above is provided, and the irradiation means and the narrow-range photographing means share the deflection means.
(2) An ophthalmic laser treatment device for treating a patient's eye, which is an irradiation means for irradiating the patient's eye with a laser beam for treatment and a narrow area for taking a narrow-area fundus image of the patient's eye. It is characterized in that the imaging means is provided, and the imaging position of the narrow range imaging means is linked to the irradiation position of the laser beam by the irradiation means.

According to the present disclosure, the treatment site can be confirmed in detail.

It is a schematic block diagram of the laser treatment apparatus for ophthalmology. It is a figure which shows an example of the wide-area fundus image displayed on the display part. It is a figure which shows an example of the wide area fundus image and narrow area fundus image displayed on the display part.

<Embodiment>
Hereinafter, embodiments of the present disclosure will be described with reference to the drawings. The ophthalmic laser treatment device of the present embodiment (for example, the ophthalmic laser treatment device 1) treats the patient's eye. The ophthalmic laser treatment apparatus includes, for example, an irradiation unit (for example, an irradiation optical system 10), a deflection unit (for example, a deflection unit 17), and a narrow range imaging unit (for example, a narrow region imaging unit 30). The irradiation unit irradiates the patient's eye with a therapeutic laser beam, for example. The deflector deflects the laser beam. The deflecting portion sets the irradiation position of the laser beam on the patient's eye, for example, by deflecting the laser beam. The narrow-range imaging unit captures a narrow-range fundus image of the patient's eye. The irradiation unit and the narrow range imaging unit share a deflection unit. For example, the pinching area imaging unit receives the return light from the patient's eye via the deflection unit. When the laser beam is deflected by the deflecting portion, the illumination light and the return light of the narrow range photographing portion are also deflected in conjunction with it. By providing such a configuration, the ophthalmic laser treatment apparatus of the present embodiment can confirm the treatment site of the patient's eye (laser light irradiation position and its surroundings) in detail.

The laser treatment device for ophthalmology may further include an image acquisition unit (for example, a control unit 60). The image acquisition unit acquires a wide-area fundus image having a wider imaging area than the narrow-area fundus image. The image acquisition unit may include a wide area imaging unit (for example, a wide area imaging unit 40) for capturing a wide area fundus image. The image acquisition unit may read an image previously captured as a wide-area fundus image.

The device may further include a control unit (for example, a control unit 60). The control unit may specify, for example, the imaging position of the narrow area photographing unit on the wide area fundus image by comparing the wide area fundus image and the narrow area fundus image. In addition, the control unit may present the specified imaging position to the operator. For example, the control unit may display the shooting position on the display unit (for example, the display unit 63). Further, the control unit may adjust the deflection amount of the deflection unit based on the specified imaging position. For example, the control unit may adjust the amount of deflection of the deflection unit so that the position designated on the wide-area fundus image is photographed by the narrow-range imaging unit.

The narrow range photographing unit may be provided with a light source for illumination. In this case, the narrow area photographing unit may receive the return light when the illumination light from the illumination light source is reflected by the fundus of the patient's eye.

The device may further include an aiming optical system. The aiming optical system projects aiming light for indicating the irradiation state of the laser light (for example, the irradiation position of the laser light, the size of the spot, the focus, etc.). In this case, the narrow area imaging unit may photograph the return light of the aiming light from the treatment site.

In the laser treatment device for ophthalmology, the imaging position of the narrow range imaging unit is linked to the irradiation position of the laser beam by the irradiation unit. That is, the photographing position of the narrow area photographing unit is moved together with the irradiation position of the laser beam or the aiming light, and the laser beam is irradiated to a predetermined position of the photographing area. As a result, the ophthalmologic laser treatment device can acquire a fundus image at the treatment site of the patient's eye, and the operator can confirm the treatment site in detail. In this case, the imaging position and the irradiation position may be linked by sharing the deflection unit between the irradiation unit and the narrow-range imaging unit, or the irradiation unit and the narrow-area imaging unit may be separated without sharing the deflection unit. The imaging position and the irradiation position may be linked by controlling the provided deflection unit in synchronization with the control unit.

<Example>
Hereinafter, examples of the ophthalmic laser treatment apparatus according to the present disclosure will be described with reference to the drawings. The ophthalmic laser treatment device 1 of the present embodiment mainly includes, for example, an irradiation optical system (laser delivery system) 10, a narrow range imaging unit 30, a wide area imaging unit 40, and a control unit 60 (see FIG. 1). .. The irradiation optical system 10 irradiates the patient's eye E with therapeutic laser light and aiming light (aiming light). The narrow-range imaging unit 30 captures a narrow-range fundus image of the patient's eye E. The wide area imaging unit 40 acquires a wide area fundus image of the patient eye E. The control unit 60 controls the ophthalmic laser treatment device 1.

<Irradiation optical system>
The irradiation optical system 10 oscillates a therapeutic laser beam, for example, and irradiates the patient's eye E with the laser beam. The irradiation optical system 10 includes, for example, a laser light source 11, a lens 12, a lens 15, a lens 16, a deflection unit 17, an objective lens 18, a focus adjustment unit 20, and the like.

The laser light source 11 emits a therapeutic laser beam. Further, the laser light source 11 of this embodiment also serves as an aiming light source. For example, the laser light source 11 emits visible aiming light. The aiming light indicates the irradiation state of the therapeutic laser light applied to the fundus Er (for example, the irradiation position of the therapeutic laser light, the size of the spot, the focus, and the like). Of course, the laser light source and the aiming light source may be provided separately. The lens 12 uses the laser light or the aiming light from the laser light source 11 as a parallel luminous flux. The lens 15 once forms an image of laser light or aiming light. The lens 16 guides the laser light or the aiming light imaged by the lens 15 to the deflection unit 17. The deflection unit 17 scans the laser beam or the aiming light on the fundus of the patient eye E. The deflection unit 17 is, for example, a galvano mirror or the like. The deflection unit 17 includes, for example, a galvano mirror for X-axis scanning and a galvano mirror for Y-axis scanning, and scans laser light or aiming light two-dimensionally on the fundus of the eye. As a result, the deflection unit 17 can set the irradiation position on the patient's eye. The objective lens 18 irradiates the patient's eye E with the laser beam or the irradiation light deflected by the deflection unit 17.

The laser light or aiming light from the laser light source 11 passes through the fiber 11a and is emitted from the fiber end 11b, then passes through the lens 12 and the dichroic mirror 50, and is transmitted through the lens 15 and the lens 16 to the deflection portion 17 and the dichroic mirror. It is reflected by 51 and focused on the fundus Er by the objective lens 18. At this time, the deflection unit 17 changes the irradiation position of the laser beam or the aiming light on the fundus.

The focus adjusting unit 20 adjusts the focus of the therapeutic laser light and the aiming light on the tissue of the patient eye E (fundus Er in this embodiment). The focus adjusting unit 20 includes, for example, a driving unit 21. The drive unit 21 moves, for example, a part or all of the irradiation optical system 10 in the optical axis direction. For example, the focus adjusting unit 20 focuses the laser light and the aiming light by integrally moving the optical system (inside the dotted line frame in FIG. 1) from the fiber end 11b to the lens 15 in the optical axis direction by the driving unit 21. To adjust.

<Narrow range shooting section>
The narrow area imaging unit 30 photographs, for example, the treatment site of the fundus Er including the irradiation position of the laser beam. For example, the narrow area imaging unit 30 photographs a part of the fundus from the front direction of the patient's eye and acquires a frontal image of the fundus. The narrow range photographing unit 30 is branched from the optical path of the irradiation optical system 10. For example, the narrow range photographing unit 30 is provided in the reflection direction of the dichroic mirror 50 arranged between the lens 12 and the lens 15. The optical axis of the narrow range photographing unit 30 is coaxial with the optical axis of the irradiation optical system 10 by the dichroic mirror 50.

The narrow range photographing unit 30 includes, for example, a light projecting optical system 30a and a light receiving optical system 30b. The projection optical system 30a, for example, projects illumination light for narrow-range imaging onto the fundus Er of the patient's eye E. The light receiving optical system 30b receives the return light when the illumination light projected by the light projecting optical system 30a is reflected by the fundus Er of the patient's eye E and returned.

The projection optical system 30a includes, for example, an illumination light source 31, a condenser lens 32, a field diaphragm 33, a lens 34, and a transmission / reception separation mirror 35. Further, the projection optical system 30a shares a part of the irradiation optical system 10 (lens 15, lens 16, deflection unit 17, objective lens 18, etc.). The illumination light source 31 emits illumination light for illuminating the fundus Er. The illumination light source 31 is arranged on the pupil conjugate surface. When a narrow-range fundus image is photographed in color, a white LED or the like is used as the illumination light source 31. The condenser lens 32 collects the illumination light. The condenser lens 32 is arranged so that the focal position is the position of the illumination light source 31. The field diaphragm 33 converts the luminous flux size of the illumination light into a size corresponding to the narrow range photographing range. The visual field diaphragm 33 is arranged on the fundus conjugate surface. The lens 34 collects the illumination light toward the transfer separation mirror 35. The transfer separation mirror 35 separates the optical path of the light projecting optical system 30a and the optical path of the light receiving optical system 30b. The transfer separation mirror 35 is arranged on the pupil conjugate surface. The transmission / reception separation mirror 35 may play a role of removing the reflected light inside the optical system by spatially separating the projected light beam and the received light beam.

The light receiving optical system 30b includes a lens 36 and a light receiving element 37. Further, the light receiving optical system 30b shares a part of the irradiation optical system 10 (lens 15, lens 16, deflection unit 17, objective lens 18, etc.) like the light projecting optical system 30a. The lens 36 collects the return light when the illumination light is reflected by the fundus Er toward the light receiving element 37. The light receiving element 37 receives the return light collected by the lens 36. The light receiving element 37 is, for example, a two-dimensional light receiving element. The light receiving signal of the light receiving element 37 is output to the control unit 60.

The luminous flux from the illumination light source 31 is focused by the condenser lens 32, passes through the field diaphragm 33, and then is focused by the lens 34 on the mirror surface of the transfer separation mirror 35. As a result, an image of the illumination light source 31 is formed on the surface of the input / output separation mirror. The light flux reflected by the transfer separation mirror 35 is further reflected by the dichroic mirror 50 and guided to the irradiation optical system 10. After that, the light is projected onto the fundus Er of the patient's eye E via the lens 15, the lens 16, the deflection portion 17, the dichroic mirror 51, and the objective lens 18 in the same manner as the laser light.

On the other hand, the return light of the illumination light reflected by the fundus Er is reflected by the dichroic mirror 50 via the objective lens 18, the dichroic mirror 51, the deflection portion 17, the lens 16, and the lens 15, and then the transfer separation mirror 35. It passes through the periphery and is focused by the lens 36 to form a fundus image on the light receiving element 37.

The arrangement of the narrow range photographing unit 30 is not limited to the above example. For example, the narrow range photographing unit 30 may be arranged somewhere on the upstream side (laser light source 11 side) of the deflection unit 17.

<Wide area photography department>
The wide area imaging unit 40 acquires, for example, a wide area fundus image of the patient eye E. The wide area photographing unit 40 includes, for example, a photographing light source 41, a condenser lens 41a, a slit plate 42, a lens 43, a scanning unit 44, an objective lens 18, an optical path branching portion 45, a lens 46, and an imaging element 47. To be equipped with. The photographing light source 41 emits light for photographing an image of a tissue (hereinafter, referred to as “photographing light”). As the photographing light source 41, for example, at least one of a laser light source, an SLD (super luminescent diode) light source, an LED, and the like can be used. A point-shaped light source may be used as the photographing light source 41. The condenser lens 41a collects the photographing light emitted from the photographing light source 41 on the slit plate 42. The imaging light source 41 of this embodiment is arranged at a position conjugate with the tissue of the patient's eye E (pupil in this embodiment). The photographing light source 41 may be a light source that emits at least one of infrared light, near infrared light, and visible light. When a light source that emits infrared light is used, shooting in a non-mydriatic state is easily performed. When a light source that emits white light is used, color photography is easily performed.

The slit plate 42 converts the photographing light into a slit-shaped luminous flux by shielding a part of the photographing light emitted from the photographing light source 41. That is, the slit plate 42 functions as a luminous flux conversion element that converts the photographing light into a slit-shaped luminous flux. The slit plate 42 is arranged, for example, on the fundus conjugate position. The slit plate 42 of this embodiment has a slit extending in a direction intersecting (orthogonal in this embodiment) in the scanning direction of the slit-shaped luminous flux by the scanning unit 44, and has a slit width in the scanning direction. The light from the slit plate 42 passes through the lens 43 and the optical path branching portion 45, and is incident on the scanning portion 44.

It is also possible to use an optical element other than the slit plate 42 as the luminous flux conversion element. For example, as the luminous flux conversion element, a cylindrical lens arranged between the photographing light source 41 and the fundus conjugate position may be adopted, and the photographed light may be focused in a line at the fundus conjugate position. As a result, the photographing light is formed into a line on the fundus Er.

The lens 43 once forms an image of the photographing light emitted from the photographing light source 41 at the front focal position of the objective lens 18. The lens 43 may be composed of one lens or a group of lenses.

The objective lens 18 guides the photographing light incident from the scanning unit 44 to the fundus Er of the patient eye E. Further, the objective lens 18 returns the return light of the photographing light reflected by the fundus Er of the patient eye E to the scanning unit 44. The objective lens 18 may be composed of one lens or a group of lenses. In this embodiment, the scanning unit 44 is arranged at a position conjugate with the pupil of the patient's eye E by the objective lens 18. The objective lens 18 is arranged on the downstream side of the scanning portion 44 (specifically, on the downstream side of the dichroic mirror 51) and on the upstream side of the patient eye E in the optical path of the photographing light. The objective lens 18 is also used as the irradiation optical system 10.

The scanning unit 44 scans the photographing light projected on the patient's eye E on the fundus. The scanning unit 44 of this embodiment scans the slit-shaped luminous flux of the photographing light in a direction intersecting the slit direction (orthogonal in this embodiment). The scanning direction may be, for example, a vertical direction or a horizontal direction. As the element constituting the scanning unit 44, at least one of a reflection mirror (for example, a galvano mirror, a polygon mirror, or a resonant scanner) or an acoustic optical element that changes the traveling direction of light can be used. Further, the scanning unit 44 may include a plurality of elements (for example, an element that scans the photographing light in the X direction and an element that scans the photographing light in the Y direction).

An optical path branching portion 45 is provided on the optical path between the lens 43 and the objective lens 18. The optical path branching portion 45 passes (or transmits) the photographing light (slit-shaped light flux in this embodiment) emitted from the photographing light source 41 and projected onto the fundus Er. Further, the optical path branching portion 45 reflects the return light of the photographing light reflected by the fundus Er and guides the light to the lens 46. The optical path branching portion 45 may be any of various beam splitters such as a perforated mirror and a half mirror.

The lens 46 forms an image of the return light of the photographing light reflected by the fundus Er of the patient's eye E on the image sensor 47. The image sensor 47 receives the return light of the photographing light reflected by the fundus Er and outputs an image pickup signal. The image sensor 47 is arranged at a position conjugate with the fundus Er of the patient eye E. The image sensor 47 of this embodiment uses a two-dimensional image sensor that receives slit-shaped reflected light.

The photographing light emitted from the photographing light source 41 passes through the slit plate 42, the lens 43, and the optical path branching portion 45, is deflected by the scanning portion 44, and then irradiates the patient's eye E through the objective lens 18. The objective lens 18 guides the photographed light to the fundus Er through the exit pupil formed in the anterior segment of the eye. The shooting light is swirled at the position of the exit pupil according to the drive of the scanning unit 44. The photographed light is reflected or scattered by the fundus Er. As a result, the return light (scattered / reflected light) from the fundus Er is emitted from the pupil as parallel light. The return light from the fundus Er is received by the image sensor 47 via the objective lens 18, the scanning unit 44, the optical path branching unit 45, and the lens 46.

The imaging light of the wide area imaging unit 40 does not have to be slit-shaped, and a line-shaped or dot-shaped light flux may be projected onto the patient's eye E.

<Control unit>
The control unit 60 performs various control processes in the ophthalmic laser treatment device 1. The control unit 60 includes a CPU 61, which is a controller that controls control, and a storage unit 62 that can store programs, data, and the like. The storage unit 62 stores a laser treatment program or the like for executing laser light irradiation to the patient's eye E. The number of control units 60 and controllers is not limited to one. A display unit 63, an operation unit 64, and the like are connected to the control unit 60. The display unit 63 displays a narrow-range fundus image taken by the narrow-range photographing unit 30, a wide-area fundus image taken by the wide-area photographing unit 40, and the like. The operation unit 64 receives the operation of the operator and outputs an operation signal to the control unit 60.

<Operation during laser treatment>
The operation when performing laser treatment using the ophthalmic laser treatment device 1 as described above will be described together with the operation method.

First, the surgeon sits the patient in a chair and secures the head with a face support (eg, chin rest and forehead rest) not shown. The surgeon operates the operation unit 64 with the contact lens attached to the patient's eye E to align the device 1 with respect to the patient's eye E. At this time, the control unit 60 displays the image acquired by the wide area photographing unit 40 on the display unit 63 at any time, and the operator adjusts the position until the fundus Er is reflected on the display unit 63. As shown in FIG. 2, when the wide-area fundus image P1 is projected on the display unit 63, the operator presses the optimize switch provided on the operation unit 64. When the optimize switch is pressed, the control unit 60 optimizes the wide-area fundus image P1. For example, the control unit 60 adjusts the focus of the wide area photographing unit 40.

After that, when the aiming light output switch provided on the operation unit 64 is pressed by the operator, the aiming light is output by the irradiation optical system 10. When the aiming light is output, as shown in FIG. 3, the display unit 63 displays the wide-area fundus image P1 captured by the wide-area photographing unit 40 and the narrow-area fundus image P2 captured by the narrow-range photographing unit 30. The imaging position of the narrow-area fundus image P2 is displayed on the wide-area fundus image P1 by the electronic frame Q. In addition, the aiming light image G can be observed in the narrow-range fundus image P2.

When the irradiation position of the laser beam is changed, the control unit 60 changes the position of the electronic frame Q on the wide-area fundus image P1 and the inclination of the deflection unit 17. Since the narrow range photographing unit 30 shares the deflection unit 17, the photographing position is changed at the same time as the irradiation position of the laser beam is changed. Since the optical axis of the narrow-range photographing unit 30 and the optical axis of the laser light are shared, the aiming light image G is always located at the center of the narrow-range fundus image P2 regardless of the inclination of the deflection unit 17. ..

As described above, the ophthalmic laser treatment device 1 of the present embodiment can clearly confirm the details of the treatment site by including the narrow area imaging unit 30. Further, by incorporating the irradiation optical system 10 rather than incorporating a completely independent narrow-range observation system, it is possible to eliminate the need for axis alignment with the laser beam and to make the overall compact configuration. Further, since the details of the treatment site can be confirmed while grasping the irradiation position of the laser beam in the entire fundus from the wide area fundus image taken by the wide area imaging unit 40, more accurate treatment can be realized. For example, in a conventional ophthalmologic laser treatment device in which a fundus imaging device and a laser photocoagulation device are integrated, it was possible to determine where the laser beam irradiation position is located on the fundus from a wide-area fundus image. However, it was difficult to observe the laser beam irradiation position (and its surroundings) in detail only with the wide-area fundus image. Although it is possible to enlarge the wide-area fundus image by digital zoom, it was difficult to observe clearly because the pixels were coarse.

<Example of transformation>
If it is obvious that the aiming light image G is located at the center of the narrow-range fundus image P2 as in the above method, the irradiation position can be specified by the narrow-range fundus image P2. Is not necessary. For example, it can be seen that the laser beam is irradiated to the center of the narrow-range fundus image P2 even when the aiming light is not irradiated. In this case, the control unit 60 may electronically display the aiming mark at the center of the narrow-range fundus image P2.

The control unit 60 may import the wide-area fundus image P1 from an external photographing device or storage device. In this case, the configuration of the wide area photographing unit 40 may be omitted. Further, the control unit 60 can make the operator grasp which part of the imported image the narrow fundus image P2 is located by matching the narrow fundus image P2 with the imported image. Further, the control unit 60 may adjust the deflection amount of the deflection unit based on the narrow area fundus image P2 imaged by the narrow area photographing unit 30 and track the imported image. Further, by omitting the configuration of the wide area imaging unit 40, a handheld type ophthalmic laser treatment device may be used. Also in this case, since the deflection portion 17 is provided, the laser beam can be irradiated with higher accuracy than the conventional slit lamp.

The light receiving optical system 30b may be used for focusing detection of laser light. In this case, the light receiving optical system 30b detects, for example, the return light when the aiming light is reflected by the fundus Er, and determines the focus state of the aiming light based on the detection result. For example, the control unit 60 determines the focus state of the aiming light based on the brightness distribution of the image of the return light acquired by the light receiving element 37. For example, when the light receiving element 37 is a two-dimensional sensor such as a CCD, the control unit 60 determines the focus state of the aiming light based on the degree of blurring (magnitude of brightness or spread of the image) of the image of the return light in the image. .. In the case of this embodiment, since the aiming light and the laser light are applied to the patient's eye E in the common optical path, determining the focus state of the aiming light is the same as determining the focus state of the therapeutic laser light. Is.

The narrow range photographing unit 30 of this embodiment is branched from the optical path of the irradiation optical system 10 instead of the wide area photographing unit 40. As a result, the magnification of the narrow area photographing unit 30 (narrow area fundus image) and the magnification of the wide area photographing unit 40 (wide area fundus image) can be set to different magnifications, so that the magnification is limited to the magnification of the wide area fundus image. It is possible to set the magnification so that the treatment site can be easily observed in detail.

In the above examples, the wide-area fundus image P1 is an infrared image and the narrow-range fundus image P2 is a color image from the viewpoint of the characteristics of the dichroic mirror and detailed observation, but the present invention is not limited to this. For example, the narrow-range fundus image P2 may also be an infrared image. In this case, for example, the reflectance of infrared light of the dichroic mirror 51 may be set to 50:50 or the like.

The aiming light image may be captured in the wide-area fundus image P1. In this case, for example, the reflectance of the aiming light of the dichroic mirror 51 may be set to 50:50 or the like.

The narrow area photographing unit 30 may include an optical system of OCT (Optical Coherence Tomography) and may take a tomographic image of the patient's eye E (for example, a two-dimensional tomographic image by B scan). In this case, an OCT deflection unit may be provided in addition to the deflection unit 17.

In the above embodiment, the arrangement of each optical system may be changed. For example, the translucent side and the reflective side of the dichroic mirror 50 or the dichroic mirror 51 may be interchanged.

When the narrow range photographing unit 30 is branched from other than the irradiation optical system, the narrow range photographing unit 30 may be provided with a deflection unit different from the deflection unit 17 of the irradiation optical system 10. In this case, the control unit 60 synchronizes the deflection unit 17 of the irradiation optical system 10 with the deflection unit of the narrow range photographing unit 30 to obtain the irradiation position of the laser light by the irradiation optical system 10 and the narrow range photographing unit 30. The shooting position of may be linked. As a result, the ophthalmic laser treatment device 1 can take a narrow-range image of the treatment site of the patient's eye.

The wide area photographing unit 40 may also be used as the narrow area photographing unit 30. In this case, for example, a narrow-area fundus image may be captured by increasing the imaging magnification of the wide-area imaging unit 40 and photographing the treatment site.

In the above-described embodiment, the example in which the treatment is performed with the contact lens worn has been described, but the treatment can be performed without wearing the contact lens.

1 Ophthalmic laser treatment device 10 Irradiation optical system 11 Laser light source 17 Deflection unit 18 Objective lens 20 Focus adjustment unit 30 Narrow range imaging unit 40 Wide area imaging unit 60 Control unit

Claims (10)

An ophthalmic laser treatment device for treating the patient's eye.
An irradiation means for irradiating the patient's eye with a therapeutic laser beam,
Deflection means for deflecting the laser beam and
A narrow-range photographing means for taking a narrow-range fundus image of the patient's eye is provided.
An ophthalmic laser treatment apparatus characterized in that the irradiation means and the narrow area photographing means share the deflection means. The ophthalmic laser treatment apparatus according to claim 1, further comprising an image acquisition means for acquiring a wide-area fundus image having a wider imaging area than the narrow-area fundus image. The ophthalmic laser treatment apparatus according to claim 2, wherein the image acquisition means includes a wide area imaging unit for capturing a wide area fundus image. The ophthalmic laser treatment apparatus according to claim 2, wherein the image acquisition means reads an image previously captured as the wide-area fundus image. 2. The second aspect of the present invention is characterized in that the control means for specifying the imaging position of the narrow area photographing means on the wide area fundus image is further provided by comparing the wide area fundus image with the narrow area fundus image. Laser treatment device for ophthalmology. The ophthalmic laser treatment apparatus according to claim 5, wherein the control means presents the specified imaging position to the operator. The ophthalmic laser treatment apparatus according to claim 5, wherein the control means adjusts the deflection amount of the deflection means based on the specified imaging position. The ophthalmic laser treatment apparatus according to any one of claims 1 to 7, wherein the narrow-range imaging means includes an illumination light source for illuminating the treatment site of the patient's eye. Further, an aiming optical system for projecting aiming light for indicating the irradiation state of the laser light is provided.
The ophthalmic laser treatment apparatus according to any one of claims 1 to 8, wherein the narrow range photographing means captures a return light of the aiming light. An ophthalmic laser treatment device for treating the patient's eye.
An irradiation means for irradiating the patient's eye with a therapeutic laser beam,
A narrow-range photographing means for taking a narrow-range fundus image of the patient's eye is provided.
An ophthalmic laser treatment apparatus characterized in that the imaging position of the narrow-range imaging means is linked to the irradiation position of the laser beam by the irradiation means.

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