JP2010148635A - Ophthalmic apparatus for laser medical treatment - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide an ophthalmic apparatus for laser medical treatment, not applying a laser beam for medical treatment to the center socket. <P>SOLUTION: This ophthalmic apparatus for laser medical treatment includes: a photo-coagulation laser device 150 oscillating a laser beam for medical treatment; a lighting optical system 100 for illuminating the fundus oculi Ef; a fixation index projection optical system 160 for projecting a fixation index on the fundus oculi Ef; an observation photographing optical system 120 for observing the fundus oculi Ef; an irradiation optical system 170 for applying the laser beam to the medical treatment region of the fundus oculi Ef; and a display part 11G for displaying a fundus oculi image observed by the observation photographing optical system 120. The irradiation optical system 170 is the ophthalmic apparatus 10 for laser medical treatment including a deflection means 141 for moving the laser beam vertically and laterally to the fundus oculi Ef. In the apparatus, the fixation point position of the fundus oculi Ef is obtained based on the projection position of the fixation index to the fundus oculi Ef by the fixation index projection optical system 160, and a region of a predetermined range surrounding the fixation point position is displayed as an irradiation-inhibited zone of the laser beam on a monitor 11. <P>COPYRIGHT: (C)2010,JPO&INPIT

Description

  The present invention relates to an ophthalmologic apparatus for laser treatment that irradiates a treatment site on the fundus with laser light.

  Conventionally, an ophthalmologic apparatus for laser treatment that performs treatment by irradiating a treatment site on the fundus with laser light is known (see Patent Document 1).

Such a laser treatment ophthalmologic apparatus scans the fundus with an observation laser beam to display a fundus image on a monitor, and designates a treatment site on the fundus image displayed on the monitor using a cursor or the like. The designated position is irradiated with therapeutic laser light.
JP 2007-181631 A

  In this laser treatment ophthalmologic apparatus, in order to reduce glare of the patient, infrared fluorescence is used for observing the fundus during treatment. When observed with this infrared fluorescence, the fovea (macular center) is observed. It becomes difficult to observe, and there is a risk that laser irradiation is mistakenly applied to the fovea, which is originally contraindicated for irradiation. In addition, there are cases where the fixation point (position) differs from the fovea for the oblique and convoluted eyes, and there was a risk of accidental irradiation around the fixation point that should not be irradiated and solidification. .

  An object of the present invention is to provide an ophthalmologic apparatus for laser treatment that does not coagulate the fovea, its periphery, and a fixation point site with a treatment laser beam.

The invention of claim 1 includes a laser beam oscillation means that oscillates a therapeutic laser beam, an illumination optical system that illuminates the fundus, a fixation target projection optical system that projects a fixation target on the fundus, and the fundus. An observation optical system for observing, an irradiation optical system for irradiating the treatment site of the fundus with the laser light, and a display unit for displaying a fundus image observed by the observation optical system, the irradiation optical system comprising: A laser treatment ophthalmologic apparatus having a deflection means for deflecting laser light vertically and horizontally with respect to the fundus,
Based on the fixation target projection position on the fundus by the fixation target projection optical system, the fundus fixation point position is determined,
An area of a predetermined range surrounding the fixation point position is displayed on the display unit as the laser light irradiation prohibited area.

  According to the present invention, it is possible to prevent the central fovea, the periphery thereof, and the fixation point site from being solidified by the therapeutic laser beam.

  Hereinafter, an embodiment as an embodiment of an ophthalmologic apparatus for laser treatment according to the present invention will be described with reference to the drawings.

[Constitution]
The laser treatment ophthalmologic apparatus 10 shown in FIG. 1 includes a photocoagulation laser device (laser light oscillation means) 150 that oscillates a treatment laser beam (photocoagulation laser beam) and illumination optics that illuminates the fundus oculi Ef of the eye E to be examined. A system 100, an observation photographing optical system (observation optical system) 120 for observing and photographing the fundus oculi Ef, a fixation target projection optical system 160 that projects a fixation target on the fundus oculi Ef, and a photocoagulation laser device 150. Based on the irradiation optical system 170 that irradiates the treatment site of the fundus oculi Ef, the monitor (display unit) 11 that displays the fundus image observed by the observation imaging optical system 120, and the projection position of the fixation target on the fundus oculi Ef. And an arithmetic and control unit 200 that obtains a foveal position and displays a predetermined region centered on the foveal position on the monitor 11 as a laser light irradiation prohibited area.

  The illumination optical system 100, the observation photographing optical system 120, the fixation target projection optical system 160, and the irradiation optical system 170 are incorporated in a laser treatment ophthalmic apparatus main body (fundus camera main body) 311. A base table (not shown) provided with a subject's chin rest (not shown), and a left-right direction (X direction) with respect to the subject's eye E of the chin rest; It can move in the vertical direction (Y direction) and the front-back direction (Z-axis direction).

  The monitor 11 is attached to the fundus camera body 311 so that the examiner can observe a fundus image Ef ′ displayed on the display screen (display unit) 11G of the monitor 11.

  The photocoagulation laser device 150 oscillates laser light having a wavelength of, for example, 532 nm (treatment laser light), and this laser light is introduced into the optical fiber 152 and emitted from the emission end 152a.

  The illumination optical system 100 includes a light source such as a halogen lamp 101 and a xenon lamp 103, condenser lenses 102 and 104 that collect illumination light from the light source, exciter filters 105 and 106, a ring translucent plate 107, and a mirror 108. An LCD 109, an illumination stop 110, a relay lens 111, a perforated mirror 112, an objective lens 13, and the like.

  The halogen lamp 101 emits light when observing the fundus oculi Ef, and the xenon lamp 103 emits light as flash light when photographing the fundus oculi Ef.

  The exciter filter 105 is disposed on the optical path during FAG (fluorescein fluorescence imaging) imaging, and the exciter filter 106 is disposed on the optical path during ICG (indocyanine green fluorescence imaging) imaging. The exciter filters 105 and 106 are inserted into and removed from the optical path by a solenoid (not shown), and are removed from the optical path during color observation and photographing.

  The ring light transmitting plate 107 is disposed at a position conjugate with the pupil of the eye E to be examined, and has a ring through hole portion 107 a centering on the optical axis of the illumination optical system 100.

  The LCD 109 displays a fixation target (not shown) for fixing the eye E to be examined.

  The illumination stop 110 is a stop member that blocks part of the illumination light to prevent flare and the like, and is movable in the optical axis direction. By this movement, the illumination area of the fundus oculi Ef is adjusted.

  The perforated mirror 112 is an optical element that synthesizes the optical axis of the illumination optical system 100 and the optical axis of the observation photographing optical system 120, and has a hole 112a in the center region.

  The observation photographing optical system 120 includes an objective lens 13, a perforated mirror 112, a photographing aperture 121, barrier filters 122 and 123, a variable power lens 124, a relay lens 125, a photographing lens 126, a mirror 134, Field lens 128, half mirror 135, relay lens 131, dichroic mirror 136, photographing lens 133, imaging device 20 such as a television camera, reflection mirror 137, photographing lens 138, and imaging device such as a television camera 12 mag.

  The barrier filter 122 is disposed on the optical path during FAG imaging, and the barrier filter 123 is disposed on the optical path during ICG imaging. The barrier filters 122 and 123 are inserted into and removed from the optical path by a solenoid (not shown), and are removed from the optical path during color observation and photographing.

  The variable magnification lens 124 can be moved in the optical axis direction of the observation photographing optical system 120 by a driving mechanism (not shown). By changing the magnification lens 124 in the optical axis direction, the observation magnification and the imaging magnification are changed, and the fundus image is focused.

  The dichroic mirror 136 transmits illumination light having a wavelength in the visible region (visible light having a wavelength of about 400 nm to 700 nm) and illumination light having a wavelength in the near infrared region (near infrared light having a wavelength of about 700 nm to 800 nm). Is supposed to be reflected.

  The imaging device 20 has an imaging element 20a such as a CCD or a CMOS. The image sensor 20a has sensitivity to near infrared light. That is, the imaging device 20 is a so-called infrared camera.

  The imaging device 20 is configured to send an image signal of the captured fundus image of near-infrared light to the arithmetic control device 200 and the monitor 11.

  The monitor 11 displays a fundus image Ef ′ of near infrared light on the display screen 11G based on the image signal from the imaging device 20.

  A touch panel 11T is attached to the display screen 11G of the monitor 11, and a laser light irradiation prohibited area can be set by a touch operation of the touch panel 11T. The touch signal of the touch panel 11T is sent to the arithmetic and control unit 200.

  The imaging device 12 has an imaging element 12a such as a CCD or a CMOS. This image sensor 12a has a sensitivity of visible light. That is, the imaging device 12 is a so-called normal television camera.

  The fixation target projection optical system 160 includes an LCD 140 that displays an internal fixation target, a condensing lens 139, a half mirror 135, a field lens 128, a mirror 134, a photographing lens 126, a relay lens 125, and a variable lens. A double lens 124, a photographing aperture 121, a perforated mirror 112, and an objective lens 13 are included.

  The irradiation optical system 170 condenses the laser light emitted from the emission end 152a of the optical fiber 152 into a parallel light beam, and the laser light converted into the parallel light beam by the lens 142 at any part of the fundus oculi Ef. , A dichroic mirror 136, a relay lens 131, a half mirror 135, a field lens 128, a mirror 134, a photographing lens 126, a relay lens 125, and a variable magnification A lens 124, a photographing aperture 121, a perforated mirror 112, an objective lens 13, and the like are included.

  As shown in FIG. 2, the deflection unit 141 includes a horizontal galvano mirror 141A for deflecting laser light in the horizontal direction, a vertical galvano mirror 141B for deflecting laser light in the vertical direction, and mirrors 141C and 141D. is doing.

  The horizontal galvanometer mirror 141A deflects the laser beam in the horizontal direction by rotating about an axis 141a parallel to the paper surface. The vertical galvanometer mirror 141B deflects the laser beam in the vertical direction by rotating about an axis 141b in a direction orthogonal to the paper surface.

  And the irradiation part of the laser beam on the fundus oculi Ef is determined by the rotation angle of the horizontal galvanometer mirror 141A and the vertical galvanometer mirror 141B.

  The horizontal galvanometer mirror 141A and the vertical galvanometer mirror 141B are rotated by mirror drive mechanisms 241 and 242 shown in FIG.

  As shown in FIG. 3, the arithmetic and control unit 200 forms a fundus image based on the control unit 210 that controls the mirror driving mechanisms 241 and 242, the photocoagulation laser unit 150, and the image signals from the imaging units 10 and 12. An image forming unit 220 that performs the processing, an image processing unit 230, and the like.

  Based on the operation of the operation unit, the control unit 210 inserts / detaches the exciter filters 105 and 106 and the barrier filters 122 and 123 into the optical path, moves the variable power lens 124 in the optical axis direction, the halogen lamp 101 and the xenon lamp. 103 is controlled to emit light.

The image processing unit 230 forms an irradiation prohibited area image indicating an irradiation prohibited area from the position of the fixation target or the position of the fovea, and various images based on a signal output from the touch panel 11T and an operation of the operation unit 300. Or form. Various images formed by the image processing unit 230 are superimposed on the fundus image and displayed on the monitor 11.
[Operation]
Next, the operation of the laser treatment ophthalmologic apparatus 10 configured as described above will be described.

  First, the exciter filters 105 and 106 and the barrier filters 122 and 123 are separated from the optical path, and the reflection mirror 137 is inserted at the broken line position (optical path). Next, the halogen lamp 101 is caused to emit light. Illumination light emitted from the halogen lamp 101 passes through the condenser lenses 102 and 104, the ring translucent plate 107, the mirror 108, the LCD 109, the illumination aperture 110, the relay lens 111, the perforated mirror 112, and the objective lens 13. Illuminate the fundus oculi Ef.

  The illumination reflected light that illuminates the fundus oculi Ef includes the objective lens 13, the perforated mirror 112, the photographing aperture 121, the variable power lens 124, the relay lens 125, the photographing lens 126, the mirror 134, the field lens 128, the half mirror 135, and the relay lens. 131, the dichroic mirror 136, the reflection mirror 137, and the photographing lens 138 reach the image pickup device 12a of the image pickup apparatus 12, and a fundus image is formed on the image pickup device 12a.

  An image signal of a fundus image is output from the imaging device 12 and input to the image forming unit 220 of the arithmetic and control unit 200. The image forming unit 220 forms a fundus image based on the input image signal, and this fundus image Ef ′ is displayed on the display screen 11G of the monitor 11 as shown in FIG. Further, on the display screen 11G of the monitor 11, a boundary line image L3 indicating the laser beam irradiation possible range is displayed on the display screen 11G of the monitor 11. This is for irradiating the fundus oculi Ef through the hole 112a of the perforated mirror 112 with a laser beam, so that the irradiation range is limited. This is to inform the examiner of this and make the irradiation range easy to understand.

  When a fixation target is displayed on the LCD 140 by operating the operation unit 300, the fixation target is converted into a condenser lens 139, a half mirror 135, a field lens 128, a mirror 134, a photographing lens 126, a relay lens 125, and a variable power lens. 124, the imaging aperture 121, the perforated mirror 112, and the objective lens 13. And it calculates from the display position information of LED140, and as shown in FIG. 4, the fixation target K is displayed on the fundus image Ef 'on the display screen 11G of the monitor 11.

  When the fixation target K is visually recognized by the subject, when the eye E is normal, the fixation point and the fovea Q coincide with each other, so that the fixation target K and the fovea Q of the eye E coincide with each other. To do. The fovea Q is observed as a small black spot.

  When the eye E is not normal, that is, when the fixation point and the fovea Q are misaligned due to strabismus or corneal abnormality, the fixation target K and the fovea Q are misaligned as shown in FIG. It is displayed on the image Ef ′. Note that the point P in the fixation target K is the fixation point.

  When the fixation point can be confirmed, the confirmation key of the operation unit 300 is operated to confirm the fixation of the fixation point, for example.

  When the confirmation key is operated, the control unit 210 obtains the position of the fixation target K based on the image formed by the image forming unit 220 by calculation processing. When the fixation target K (fixation viewpoint P) and the fovea Q are misaligned, the positions of the fixation target K and the fovea Q are obtained. That is, the control unit 210 has functions of a fixation target position detection unit that determines the position of the fixation target K and a foveal position detection unit that calculates the position of the fovea Q.

  When the position of the fixation target K is obtained, the image processing unit 230 forms a boundary line image L1 indicating an irradiation prohibited area in which laser light irradiation around the fixation target K that is the fixation point is prohibited. The boundary line image L1 is displayed on the display screen 11G of the monitor 11 as shown in FIG. Laser irradiation is prohibited in the boundary line image L1.

  When the fixation target K and the fovea Q are misaligned, in addition to the boundary line image L1, a boundary indicating an irradiation prohibited area (irradiation prohibited range) for prohibiting laser light irradiation around the fovea Q A line image L2 is formed, and this boundary line image L2 is displayed together with the boundary line image L1 on the display screen 11G of the monitor 11 as shown in FIG. Laser light irradiation is also prohibited in the boundary line image L2.

  The width of the area indicated by the boundary line images L1 and L2 is set in advance, but the width of the area, that is, the size of the diameter of the boundary line images L1 and L2 can be changed by the operation of the operation unit 300. It has become. When the magnification is changed by the magnification lens 124, the diameters of the boundary line images L1 and L2 are changed according to the magnification.

  In the boundary line images L1 and L2, the control unit 210 performs a control operation so that a treatment area cannot be set. That is, the control unit 210 prohibits the setting of the treatment area (treatment area setting prohibition means) and the irradiation prohibition that prohibits the irradiation of the laser beam toward the fundus corresponding to the irradiation prohibited area (irradiation prohibited range). It has a function as a means.

  Data indicating the position (fixation position or foveal position) and size of each of the boundary line images L1 to L3 is stored in a memory (not shown).

  Thereafter, when infrared fluorescence observation is performed, a fluorescent agent is intravenously administered to the subject in advance.

  Then, the infrared fluorescent mode is set by operating the operation unit. With this infrared fluorescence mode, the exciter filter 106 of the illumination optical system 100 is inserted into the optical path, and the barrier filter 123 of the observation photographing optical system 120 is inserted into the optical path.

  By inserting the exciter filter 106 into the optical path, only visible light having a predetermined wavelength illuminates the fundus oculi Ef as excitation light.

  When the fluorescent agent flows into the blood vessel of the fundus oculi Ef, the fluorescent agent emits infrared fluorescence by the excitation light, and this infrared fluorescence is emitted from the objective lens 13, the perforated mirror 112, the photographing aperture 121, and the barrier filter. 123, the zoom lens 124, the relay lens 125, the photographing lens 126, the mirror 134, the field lens 128, the half mirror 135, and the relay lens 131, and reaches the dichroic mirror 136, and is reflected by the dichroic mirror 136. The infrared fluorescence reflected by the dichroic mirror 136 reaches the image pickup device 20a of the image pickup apparatus 20 via the photographing lens 133, and a fundus image is formed on the image pickup device 20a.

  Then, as shown in FIG. 8, a fundus image Ef ″ by infrared fluorescence is displayed on the display screen 11G of the monitor 11. This fundus image Ef ″ is infrared fluorescence emitted from the fluorescent agent that has flowed into the blood vessel. As a result, it is an image of the choroid under the retina, and thus the fovea Q (see FIGS. 4 and 5) and the nipple on the retina do not appear on the display screen 11G. Further, since the visible light is cut by the barrier filter 123, the fixation target K is not displayed on the display screen 11G.

  On the display screen 11G of the monitor 11, the boundary line image L1 and the boundary line image L3 are displayed on the fundus oculi image Ef ″ based on the data stored in the memory.

  When the fixation target K and the fovea Q are misaligned, a boundary image L2 is displayed in addition to the boundary line images L1 and L3, as shown in FIG.

  Next, the fixation target is displayed on the LCD 109 at the same position as the fixation target K displayed on the LCD 140, and the subject is visually recognized.

  Accordingly, the positions of the boundary line images L1 and L3 with respect to the fundus image Ef ″ shown in FIG. 8 are the same as the positions with respect to the fundus image Ef ′ shown in FIG. The fovea Q of the fundus oculi Ef (see FIG. 4) is located at the position, and the laser beam irradiation range indicated by the boundary line image L3 in FIG. 8 and the laser beam irradiation range indicated by the boundary line image L3 in FIG. Matches the fundus oculi Ef.

  Even when the fixation target K and the fovea Q are misaligned, the boundary line images L1, L2, and L3 shown in FIG. 9 and the boundary line images L1, L2, and L3 shown in FIG. Will be displayed in the position. That is, the fixation point P (see FIG. 5) of the fundus oculi Ef is located at the center of the boundary line image L1 shown in FIG. 9, and the fovea Q is located at the center position of the boundary line image L2.

  Next, the examiner searches for a treatment site from the fundus oculi image Ef ″ displayed on the display screen 11G shown in FIG. 8 or FIG. 9, and sets a treatment region to be irradiated with laser light.

  The treatment area is set by touching the touch panel 11T on the display screen 11G of the monitor 11 to set the treatment area (irradiation area). When this treatment area is set, a boundary line image L4 indicating the treatment area is displayed on the fundus oculi image Ef ″ of the display screen 11G of the monitor 11 as shown in FIG. 8 or FIG.

  In this case, a signal from the touch panel 11T is input to the control unit 210 of the arithmetic and control unit 200, and the boundary line image L4 is formed by the image processing unit 230.

  At the time of this setting, since the boundary line image L3 indicating the laser beam irradiation possible range is displayed on the display screen 11G of the monitor 11, it is possible to prevent the setting of a portion not irradiated with the laser beam. it can.

  Further, when the treatment area enters the boundary line images L1 and L2 indicating the irradiation prohibited areas, the treatment area cannot be set in the boundary line images L1 and L2. L2 is excluded and set. For example, a part of the boundary line image L4 is curved and displayed so that the boundary line images L1 and L2 do not enter.

  When the setting of the treatment area is completed, the irradiation mode is set. With this irradiation mode setting, the arithmetic and control unit 200 drives the photocoagulation laser device 150 to oscillate laser light. Further, the reflecting mirror 137 is switched to the position of the solid line so as to be separated from the optical path, and the barrier filter 123 is separated from the optical path.

  When the irradiation start key of the operation unit 300 is operated, the control unit 210 of the arithmetic control device 200 controls the mirror drive mechanisms 241 and 242 based on the treatment area set by the touch panel 11T. This control is to control the rotation angle of the horizontal galvanometer mirror 141A and the vertical galvanometer mirror 141B so that the laser beam irradiates only the range in the boundary line image L4.

  On the other hand, the laser light oscillated by the photocoagulation laser device 150 is introduced into the optical fiber 152, and the laser light introduced into the optical fiber 152 is emitted from the emission end face 152 a of the optical fiber 152. The laser light emitted from the emission end face 152a is a lens 142, a deflection unit 141, a dichroic mirror 136, a relay lens 131, a half mirror 135, a field lens 128, a mirror 134, a photographing lens 126, a relay lens 125, and a variable power lens 124. The treatment site of the fundus oculi Ef of the eye E is irradiated through the imaging aperture 121, the hole 112a of the perforated mirror 112, and the objective lens 13.

  The control unit 210 controls the mirror driving mechanisms 241 and 242 so that the rotation angles of the horizontal galvano mirror 141A and the vertical galvano mirror 141B are within a predetermined range based on the treatment region set by the touch panel 11T. Thus, only the range within the boundary image L4 is irradiated with the laser light.

  The irradiation pattern of the laser beam in the boundary line image L4 is irradiated in a dot shape at regular intervals, for example. The timing of introducing the laser light into the optical fiber 152 is performed using an acousto-optic modulator or the like.

  As described above, at the time of infrared fluorescence observation, the fovea Q and the fixation target K of the fundus oculi Ef do not appear on the display screen 11G of the monitor 11 as shown in FIGS. Since boundary image L1, L2 which shows the irradiation prohibition area of a predetermined range centering on the viewpoint P is displayed on the display screen 11G, it prevents that the fovea Q and the fixed viewpoint P are irradiated with a laser beam. be able to.

  Moreover, the boundary line images L1 and L2 cannot be set as treatment regions, and the control unit 210 further includes a mirror driving mechanism so that the laser beam does not irradiate the boundary line images L1 and L2. Since 241 and 242 are controlled, the ophthalmic apparatus 10 for laser treatment with higher safety is obtained.

  In the above embodiment, the treatment area cannot be set as the irradiation prohibited area in the boundary line images L1 and L2, but the irradiation prohibited area can be canceled and only the display can be performed by the switching operation of the switch. You may comprise. Further, the diameters of the boundary line images L1 and L2 may be changed according to the diopter of the eye E to be examined. In this case, the diameters of the boundary line images L1 and L2 are increased as the diopter (diopter) is increased.

  In the above embodiment, the laser treatment ophthalmologic apparatus 10 in which the fundus camera is provided with the laser irradiation unit (the photocoagulation laser device 150, the lens 142, and the deflection unit 141) has been described. A laser treatment ophthalmologic apparatus may be configured by providing the laser irradiation unit.

It is an optical arrangement | positioning figure which showed the structure of the ophthalmologic apparatus for laser treatment concerning this invention. It is explanatory drawing which showed the structure of the deflection | deviation unit. It is the block diagram which showed the structure of the control system of the ophthalmologic apparatus for laser treatment. It is explanatory drawing which showed the fundus image displayed on the display screen of a monitor, and a fixation target. It is explanatory drawing of the fundus image which showed the case where the fovea of the fundus is out of alignment with the fixation point. FIG. 5 is an explanatory diagram illustrating an example in which a boundary line image indicating an irradiation prohibited area is displayed on the fundus image illustrated in FIG. 4. It is explanatory drawing which showed an example which displayed the boundary line image which shows an irradiation prohibition area on the fundus image shown in FIG. It is explanatory drawing which showed the boundary line image which shows the fundus image by infrared fluorescence, and an irradiation prohibition area. It is explanatory drawing which showed the boundary line image which shows the fundus image and infrared rays prohibition area by infrared fluorescence in the case where the fovea of the fundus is out of alignment with the fixed viewpoint.

Explanation of symbols

DESCRIPTION OF SYMBOLS 10 Laser treatment ophthalmic apparatus 11 Monitor 100 Illumination optical system 120 Observation imaging | photography optical system (observation optical system)
141 Deflection unit (deflection means)
150 Photocoagulation laser device (laser light oscillation means)
160 Fixation target projection optical system 170 Irradiation optical system 200 Arithmetic control device E Eye to be examined Ef Fundus

Claims (7)

Laser light oscillation means for oscillating therapeutic laser light, illumination optical system for illuminating the fundus, fixation target projection optical system for projecting a fixation target on the fundus, and observation optical system for observing the fundus, An irradiation optical system that irradiates the treatment site of the fundus with the laser light; and a display unit that displays a fundus image observed by the observation optical system, wherein the irradiation optical system applies the laser light to the fundus An ophthalmologic apparatus for laser treatment having deflection means for deflecting vertically and horizontally,
Based on the fixation target projection position on the fundus by the fixation target projection optical system, the fundus fixation point position is determined,
An ophthalmologic apparatus for laser treatment, wherein an area within a predetermined range surrounding the fixation point position is displayed on the display unit as a laser light irradiation prohibited area.   2. The ophthalmologic apparatus for laser treatment according to claim 1, wherein the irradiation optical system prohibits laser light irradiation toward the fundus corresponding to the irradiation prohibited area displayed on the display unit. A touch panel that is attached to the display unit and that designates an irradiation region of the laser light based on a fundus image displayed on the display unit;
3. The ophthalmologic apparatus for laser treatment according to claim 1, wherein in the irradiation prohibited area displayed on the display unit, designation of an irradiation area is prohibited by the touch panel.   The fovea is obtained based on a fundus image obtained by the observation optical system, and a predetermined range surrounding the fovea is displayed on the display unit as a laser beam irradiation prohibited range. The ophthalmic apparatus for laser treatment according to any one of the above.   5. The ophthalmologic apparatus for laser treatment according to claim 4, wherein the irradiation optical system prohibits laser light irradiation toward the fundus corresponding to an irradiation prohibited range displayed on the display unit.   The ophthalmologic apparatus for laser treatment according to any one of claims 1 to 3, wherein the size of the irradiation prohibited area can be changed.   6. The ophthalmologic apparatus for laser treatment according to claim 4, wherein the size of the irradiation prohibited range can be changed.

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