JP2024049898A - Ophthalmic laser treatment apparatus and ophthalmic laser treatment program - Google Patents

Abstract

To provide an ophthalmic laser treatment apparatus and an ophthalmic laser treatment program which can excellently adjust an irradiation position to a portion with a small structural feature.SOLUTION: An ophthalmic laser treatment apparatus for treating a patient eye comprises: irradiation means which irradiates the patient eye with laser light for treatment or sight; adjustment means which adjusts the irradiation position of the laser light; an observation optical system which acquires an observation image by imaging the patient eye; detection means which detects a positional deviation of the irradiation position in the direction vertical to an optical axis of the laser light on the basis of a reference image that becomes the reference for adjusting the irradiation position to the patient eye and the observation image; and control means which controls the adjustment means and corrects the irradiation position on the basis of the positional deviation detected by the detection means. The control means updates the reference image with the observation image.SELECTED DRAWING: Figure 4

Description

The present disclosure relates to an ophthalmic laser treatment device that treats a patient's eye by irradiating it with laser light, and an ophthalmic laser treatment program.

An ophthalmic laser treatment device is known for irradiating a patient's eye with laser light to treat the patient's eye (see Patent Document 1).

JP 2015-006402 A

Meanwhile, a new ophthalmic laser treatment device has been developed that combines an ophthalmic imaging device with a laser treatment device. In such devices, the irradiation position is aligned based on structural features of the blood vessels and optic disc of the fundus photographed by the ophthalmic imaging device.

However, when there are few structural features around the treatment area, it is difficult to align the irradiation position.

In consideration of the problems with the conventional technology, the technical objective of this disclosure is to provide an ophthalmic laser treatment device and an ophthalmic laser treatment program that can accurately align the irradiation position even in areas with few structural features.

To solve the above problems, the present disclosure is characterized by having the following configuration:

(1) An ophthalmic laser treatment device for treating a patient's eye, comprising: an irradiation means for irradiating the patient's eye with treatment or aiming laser light; an adjustment means for adjusting the irradiation position of the laser light; an observation optical system for photographing the patient's eye to obtain an observation image; a reference image that serves as a reference for aligning the irradiation position with respect to the patient's eye; a detection means for detecting a positional deviation of the irradiation position in a direction perpendicular to the optical axis of the laser light based on the observation image; and a control means for controlling the adjustment means and correcting the irradiation position based on the positional deviation detected by the detection means, wherein the control means updates the reference image using the observation image.
(2) An ophthalmic laser treatment device for treating a patient's eye, comprising: an irradiation means for irradiating the patient's eye with treatment or aiming laser light; an adjustment means for adjusting an irradiation position of the laser light; an aiming light receiving means for receiving return light of the aiming light reflected by the patient's eye; a detection means for detecting a positional deviation of the irradiation position in a direction perpendicular to an optical axis of the laser light based on a change in luminance of the return light received by the aiming light receiving means; and a control means for controlling the adjustment means and correcting the irradiation position based on the positional deviation detected by the detection means.
(3) An ophthalmic laser treatment program executed in an ophthalmic laser treatment device for treating a patient's eye, characterized in that the program is executed by a control means of the ophthalmic laser treatment device to cause the ophthalmic laser treatment device to execute the following steps: an irradiation step of irradiating the patient's eye with treatment or aiming laser light; an adjustment step of adjusting the irradiation position of the laser light; an image acquisition step of photographing the patient's eye to acquire an observation image; a detection step of detecting a positional deviation of the irradiation position in a direction perpendicular to the optical axis of the laser light based on a reference image serving as a reference for aligning the irradiation position with respect to the patient's eye and the observation image; a correction step of correcting the irradiation position based on the positional deviation detected in the detection step; and an update step of updating the reference image using the observation image.
(4) An ophthalmic laser treatment program executed in an ophthalmic laser treatment device for treating a patient's eye, characterized in that the program is executed by a control means of the ophthalmic laser treatment device to cause the ophthalmic laser treatment device to execute an irradiation step of irradiating the patient's eye with treatment or aiming laser light, an adjustment step of adjusting the irradiation position of the laser light, an aiming light receiving step of receiving return light of the aiming light reflected by the patient's eye, a detection step of detecting a positional deviation of the irradiation position in a direction perpendicular to the optical axis of the laser light based on a change in luminance of the return light received in the aiming light receiving step, and a correction step of correcting the irradiation position based on the positional deviation detected in the detection step.

This disclosure allows the irradiation position to be optimally aligned with the treatment area.

1 is a schematic diagram of an ophthalmic laser treatment device. FIG. 13 is a diagram showing the aiming light reflected in an observation image. FIG. 4 is a flowchart showing a control operation.

<Example>
An ophthalmic laser treatment device 1 according to the present disclosure will be described below with reference to the drawings. The ophthalmic laser treatment device 1 mainly includes, for example, an irradiation optical system 10, an aiming light receiving optical system 30, an observation optical system 40, and a controller 60 (see FIG. 1). The irradiation optical system 10 irradiates a patient's eye E with a treatment laser beam and an aiming light. The aiming light receiving optical system 30 detects return light of the aiming light reflected by the fundus Er of the patient's eye E. The observation optical system 40 observes the fundus of the patient's eye. The controller 60 controls the ophthalmic laser treatment device 1.

<Irradiation optical system>
The irradiation optical system 10, for example, oscillates a treatment laser light and irradiates the laser light to the patient's eye E. 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 treatment laser light. In this embodiment, the laser light source 11 also serves as an aiming light source. For example, the laser light source 11 emits a visible aiming light. The aiming light indicates the irradiation state of the treatment laser light irradiated to the fundus (for example, the size and focus of the spot of the treatment laser light). Of course, the laser light source and the aiming light source may be provided separately. The lens 12 converts the laser light or aiming light from the laser light source 11 into a parallel light beam. The lens 15 first forms an image of the laser light or aiming light. The lens 16 guides the laser light or aiming light formed by the lens 15 into a parallel light beam to the deflection unit 17. The deflection unit 17 scans the laser light or aiming light on the fundus of the patient's eye. The deflection unit 17 is, for example, a galvanometer mirror. The deflection unit 17 includes, for example, a galvanometer mirror for X-axis scanning and a galvanometer mirror for Y-axis scanning, and two-dimensionally scans the laser light or the aiming light on the fundus. The objective lens 18 irradiates the patient's eye with the laser light 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 lens 12 and the beam splitter 50, passes through the lenses 15 and 16, is reflected by the deflection unit 17 and the dichroic mirror 51, and is focused on the fundus Er via the objective lens 18. At this time, the deflection unit 17 changes the irradiation position of the laser light or aiming light on the fundus. In this way, the deflection unit 17 functions as an adjustment means for adjusting the irradiation position of the laser light.

The focus adjustment unit 20 adjusts the focus of the treatment laser light and the aiming light in the tissue of the patient's eye (the fundus in this embodiment). The focus adjustment unit 20 includes, for example, a drive 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 adjustment unit 20 adjusts the focus of the laser light and the aiming light by integrally moving the optical system from the laser light source 11 to the lens 15 (within the dotted frame in FIG. 1) in the optical axis direction using the drive unit 21. Note that when the laser light source and the aiming light source are provided separately, the focus position of the laser light and the focus position of the aiming light may be different in the Z direction.

<Aiming light receiving optical system>
The aiming light receiving optical system 30 includes an imaging lens 31 and a light receiving element 32. The imaging lens 31 forms an image of the return light when the aiming light is reflected by the fundus Er. The light receiving element 32 receives the image of the return light formed by the imaging lens 31. The light receiving element 32 is, for example, a two-dimensional sensor such as a CCD. The light receiving element 32 outputs a light receiving signal of the aiming light to the control unit 60. The aiming light receiving optical system 30 is branched off from the optical path of the irradiation optical system 10. For example, the aiming light receiving optical system 30 is provided in the reflection direction of a beam splitter 50 arranged between the lens 12 and the lens 15. Therefore, the return light of the aiming light irradiated to the fundus Er is reflected by the dichroic mirror 51 and the deflection unit 17 via the objective lens 18, passes through the lens 16 and the lens 15, and is reflected by the beam splitter 50. The return light reflected by the beam splitter 50 is imaged by the imaging lens 31 and received by the light receiving element 32. By increasing the magnification of the aiming light receiving optical system 30, the range that can be detected with respect to the entire fundus becomes narrower, but since detection can be performed with high resolution relative to the laser spot size of the aiming light, the luminance distribution of the image of the return light can be obtained more accurately.

<Observation optical system>
The observation optical system 40 captures, for example, an observation image of the subject's eye. The observation optical system 40 includes, for example, an imaging 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 unit 45, a lens 46, and an image sensor 47. The imaging light source 41 emits light for capturing an image of tissue (hereinafter, referred to as "imaging light"). For the imaging light source 41, for example, at least one of a laser light source, an SLD (super luminescent diode) light source, an LED, etc. may be used. For the imaging light source 41, a point-like light source may be used. The condenser lens 41a collects the imaging light emitted from the imaging light source 41 onto the slit plate 42. The imaging light source 41 of this embodiment is disposed at a position conjugate with the tissue of the patient's eye E (the pupil in this embodiment). The imaging light source 41 may be a light source that emits at least one of infrared light and visible light. The imaging light source 41 may be a light source that simultaneously emits visible light and infrared light. When a light source that emits infrared light is used, imaging in a non-mydriatic state is easily performed. When a light source that emits white light (visible light) is used, color imaging is easily performed. Moreover, when imaging coagulation spots, imaging using visible light is suitable.

The slit plate 42 converts the imaging light emitted from the imaging light source 41 into a slit-shaped light beam by blocking a portion of the imaging light. In other words, the slit plate 42 functions as a light beam conversion element that converts the imaging light into a slit-shaped light beam. The slit plate 42 is disposed, for example, at a fundus conjugate position. The slit plate 42 in this embodiment has a slit that extends in a direction intersecting (orthogonal in this embodiment) the scanning direction of the slit-shaped light beam 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 unit 45 and is incident on the scanning unit 44.

It is also possible to use an optical element other than the slit plate 42 as the light beam conversion element. For example, a cylindrical lens disposed between the imaging light source 41 and the fundus conjugate position may be used as the light beam conversion element, and the imaging light may be focused in a line shape at the fundus conjugate position. As a result, the imaging light is shaped in a line shape on the fundus Er.

The lens 43 first forms an image of the photographic light emitted from the photographic light source 41 at the front focal position of the objective lens 18. The lens 43 may be composed of a single 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's eye E. The objective lens 18 also returns the return light of the photographing light reflected by the fundus Er of the patient's 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 objective lens 18 positions the scanning unit 44 at a position conjugate with the pupil of the patient's eye E. The objective lens 18 is positioned downstream of the scanning unit 44 (more specifically, downstream of the dichroic mirror 51) and upstream of the patient's 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 fundus with the imaging light projected onto the patient's eye. In this embodiment, the scanning unit 44 scans the slit-shaped light beam of the imaging light in a direction intersecting the slit direction (orthogonal in this embodiment). The scanning direction may be, for example, vertical or horizontal. The elements constituting the scanning unit 44 may be at least one of a reflecting mirror (for example, a galvanometer mirror, a polygon mirror, or a resonant scanner) and an acousto-optical element that changes the traveling direction of light. The scanning unit 44 may also include multiple elements (for example, an element that scans the imaging light in the X direction and an element that scans the imaging light in the Y direction).

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

The lens 46 forms an image on the image sensor 47 of the return light of the photographing light reflected by the fundus of the patient's eye E. The image sensor 47 receives the return light of the photographing light reflected by the fundus and outputs an image signal. The image sensor 47 is disposed at a position conjugate with the fundus of the patient's eye E. The image sensor 47 in this embodiment is 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 section 45, is deflected by the scanning section 44, and is then irradiated to the patient's eye E via the objective lens 18. The objective lens 18 guides the photographing light to the fundus Er via an exit pupil formed in the anterior segment. In response to the driving of the scanning section 44, the photographing light is rotated at the position of the exit pupil. The photographing light is reflected or scattered at the fundus Er. As a result, the return light (scattered/reflected light) from the fundus Er is emitted as parallel light from the pupil. The return light from the fundus Er is received by the image sensor 47 via the objective lens 18, the scanning section 44, the optical path branching section 45, and the lens 46.

The observation optical system 40 of this embodiment may obtain one wide-area observation image by scanning the entire fundus with slit light, or may obtain a narrow-area observation image (video) by scanning a partial area of the fundus with slit light. By narrowing the scanning area, glare for the patient can be reduced.

The observation optical system 40 may also include a variable magnification optical system for acquiring high-magnification narrow-area observation video. The variable magnification optical system is, for example, composed of multiple lenses. By including the variable magnification optical system, the fundus can be observed with higher resolution.

<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 responsible for control, and a storage unit 62 capable of storing programs, data, and the like. The storage unit 62 stores a laser treatment program and the like for irradiating the patient's eye E with laser light. The number of control units 60 and controllers is not limited to one. A display unit 63 and an operation unit 64 are connected to the control unit 60. The display unit 63 displays an observation image captured by the observation optical system 40, and the like. The operation unit 64 accepts an operation by the surgeon and outputs an operation signal to the control unit 60.

<About correcting the irradiation position>
Next, a method for correcting the irradiation position of the laser light will be described. The correction of the irradiation position is necessary, for example, when the diseased part (site to be treated) of the patient's eye is displaced from the irradiation position of the laser light due to the movement of the patient's eye. The ophthalmic laser treatment device 1 of this embodiment performs more stable correction of the irradiation position by updating the reference image that serves as a reference for positioning.

For example, the ophthalmic laser treatment device 1 of this embodiment detects the positional deviation of the irradiation position (the positional deviation of the irradiation position in a direction perpendicular to the optical axis of the laser light) by updating the reference image after laser irradiation using the coagulation spot. For example, the control unit 60 functions as a detection means for detecting the positional deviation of the irradiation position. FIG. 2(a) shows a reference image 101 taken before treatment. The reference image 101 is used, for example, to set the irradiation position of the laser light. FIG. 2(b) shows an observation image 102 taken in real time by the observation optical system 40 during treatment. The observation image 102 shows an image G of the aiming light irradiated by the irradiation optical system 10. The position of the image G of the aiming light becomes the irradiation position of the laser light. FIG. 2(c) shows a new reference image 103 taken by the observation optical system 40 after the irradiation of the laser light. The image G of the aiming light and the coagulation spot P are shown in the reference image 103.

When irradiating the laser light for the first time, the control unit 60 detects the positional deviation of blood vessels or optic discs between the reference image 101 and the observation image 102 by image processing, and corrects the irradiation position based on the detected positional deviation. When irradiating the laser light for the second time or later, the control unit 60 sets the observation image after the laser irradiation as a new reference image 103. For example, as shown in FIG. 2(d), it is assumed that the patient's eye has moved since the time when the reference image 103 was taken, and the irradiation position has shifted. In this case, the control unit 60 detects the position of the coagulation spot P in the reference image 103 and the position of the coagulation spot P in the observation image 104 taken in real time by the observation optical system 40 by image processing, and calculates the positional deviation (amount and direction) between them. The control unit 60 can easily correct the irradiation position by controlling the deflection unit 17 so that the calculated positional deviation of the coagulation spot P is offset.

In this way, by updating the reference image after laser irradiation and detecting the positional deviation of the irradiation position based on the position of the coagulation plaque P, it is possible to track the coagulation plaque P as one of the structural features even in areas with few structural features (blood vessels, optic disc, etc.). Therefore, it is possible to stably align the irradiation position with respect to the patient's eye.

<Irradiation position correction using aiming light image>
The ophthalmic laser treatment device 1 of this embodiment can also correct the irradiation position using a luminance change of the aiming light image acquired by the aiming light receiving optical system 30. The aiming light image is, for example, an image of the return light formed when the aiming light is reflected by the fundus. The control unit 60 acquires the aiming light image based on the light receiving signal of the aiming light output from the light receiving element 32. The aiming light image when the aiming light hits a lesion such as a microaneurysm has a lower luminance than the aiming light image when the aiming light hits a normal part of the fundus. Therefore, the control unit 60 may detect the deviation of the aiming light from the lesion by a luminance change of the aiming light image.

For example, FIG. 3(a) shows the aiming light image 201 in a state where the irradiation position is set at the position of the lesion D, and FIG. 3(b) shows the aiming light image 202 in a state where the irradiation position is slightly shifted from the state of FIG. 3(a). As shown in FIG. 3(a) and (b), the luminance distribution of the aiming light image 201 changes due to the shift of the irradiation position. The control unit 60 monitors the luminance of the aiming light image 202 captured in real time based on the luminance information of the aiming light image 201 at the time when the irradiation position is aligned with the lesion D to be treated. When the luminance of the real-time aiming light image 202 changes with respect to the reference aiming light image 201, the control unit 60 calculates the amount of deviation and the direction of deviation of the irradiation position by image processing or the like. For example, as shown in FIG. 3(a) and (b), the amount of deviation and the direction of deviation of the irradiation position are calculated based on the change in the position (center of gravity, etc.) of the lesion D (low luminance area) shown in the reference aiming light image 201 and the real-time aiming light image 202. The control unit 60 controls the deflection unit 17 so that the positional deviation is offset based on the calculated deviation amount and direction, and corrects the irradiation position. In this way, by detecting the positional deviation of the irradiation position based on the change in the luminance distribution of the aiming light image 201, the correction of the irradiation position can be made more stable.

<Control operation>
Next, an example of the control operation of the ophthalmic laser treatment apparatus 1 will be described with reference to the flow chart of FIG.

(Step S1: Alignment)
First, the control unit 60 adjusts (aligns) the positional relationship of the ophthalmic laser treatment device 1 with respect to the patient's eye by a driving unit (not shown). For example, the control unit 60 controls the driving unit based on an operation of the operation unit 64 by the examiner.

(Step S2: Obtaining a reference image)
The control unit 60 acquires a reference image 101 for setting an irradiation position. For example, the control unit 60 may acquire the reference image 101 by photographing the patient's eye with the observation optical system 40, or may acquire an image of the patient's eye photographed in advance by an external photographing means as the reference image 101. The control unit 60 causes the display unit 63 to display the acquired reference image 101.

(Step S3: Setting the irradiation position)
The operator operates the operation unit 64 while checking the reference image 101 displayed on the display unit 63 to set the irradiation position of the treatment laser light. At this time, the examiner may set a region where irradiation of the treatment laser light is prohibited.

(Step S4: Obtaining observed image)
The control unit 60 acquires an observation image by the observation optical system 40. The control unit 60 captures the observation image (moving image) until the treatment is completed, and displays the acquired images on the display unit 63 in real time. The observation image may be a narrow-area image. For example, the control unit 60 may capture a color fundus image by scanning the imaging light only on a part of the scanning area. In this case, for example, the control unit 60 may irradiate the scanning area including the irradiation position set in step S3 with visible light, and capture the image without irradiating the other scanning areas with the imaging light.

(Step S5: Detect deviation)
The control unit 60 compares the reference image 101 with the observation image 102 to detect a deviation in the irradiation position. For example, the deviation in the irradiation position is detected based on the positions of structural features such as blood vessels or the optic disc. Note that, if the reference image has been updated in step S8 described later, the deviation in the irradiation position may be detected based on the position of coagulation spots.

(Step S6: Irradiation position correction)
The control unit 60 corrects the irradiation position of the laser light based on the result of the detection of the positional deviation, for example, by controlling the deflection unit 17 based on the direction and amount of deviation of the irradiation position, and controls the irradiation of the laser light.

(Step S7: Irradiation of treatment laser light)
The control unit 60 irradiates the eye to be examined with the aiming light by the irradiation optical system 10. The examiner starts irradiation of the treatment laser light while finally checking the irradiation position by the aiming light reflected in the moving image of the observation image displayed on the display unit 63. The control unit 60 irradiates the treatment laser light to the set irradiation position on the fundus while correcting the irradiation position as described above based on the observation image acquired by the image sensor 47. The examiner checks the state of the irradiated area during and after laser irradiation by the observation image displayed on the display unit 63.

(Step S8: Update reference image)
The control unit 60 updates the reference image. The control unit 60 uses the observation image of the subject's eye captured after the laser light irradiation as the reference image. As a result, the coagulation spot generated at the position where the laser light was irradiated is captured in the reference image. Therefore, the control unit 60 can perform tracking using the coagulation spot as an image feature. The control unit 60 may update the reference image for each laser irradiation, or may update the reference image at a predetermined time interval.

As described above, the ophthalmic laser treatment device 1 of this embodiment can correct the irradiation position based on the positional deviation of the coagulation spot by updating the reference image. This allows for good tracking even in the absence of a distinctive fundus structure.

The ophthalmic laser treatment device 1 of this embodiment can detect deviations in the irradiation position based on changes in the luminance of the aiming light image and correct the irradiation position. This allows the laser light to be properly irradiated to the treatment area. In addition, during surgery, the operator can correct the irradiation position more easily than if the operator had to check the observation image to determine whether the irradiation position has shifted, reducing the burden on the operator.

The reference image may be updated immediately after the foot switch is pressed, or at any time interval. Since the laser light and the coagulation spots overlap, it is better not to use the observation image while the foot switch is pressed as the reference image. Also, it is preferable that the observation image used as the reference image is an image in which the aiming light is not reflected at the position of the coagulation spots, such as when the aiming light is turned off or after it has been moved.

<Example of transformation>
In step S5, the control unit 60 may detect a deviation in the irradiation position based on a luminance change in the aiming light image acquired by the aiming light receiving optical system 30. For example, as described above, when the luminance distribution of the aiming light image changes, the control unit 60 may calculate a position deviation based on the luminance change in the aiming light image and correct the irradiation position.

When updating the reference image, the control unit 60 does not need to update the entire range of the reference image. For example, only a part of the range of the reference image may be updated. For example, if the shooting range of the observation image is narrower than that of the reference image, only the range captured in the observation image may be updated.

In the above embodiment, the aiming light image is obtained by capturing an image of a narrow area irradiated with the aiming light at a high magnification using the aiming light receiving optical system 30, but this is not limited to the above. For example, the deviation of the irradiation position may be detected based on a change in the luminance distribution of a portion of a wide-area observation image in which the image G of the aiming light is captured.

As in the above embodiment, the movement of the fundus may be calculated from the observation image obtained by the observation optical system 40, and the irradiation position may be changed using this information. In other words, the observation optical system 40 may also be used in combination to adjust (track) the position of the aiming light using a scanning system in accordance with the structure of the fundus (blood vessels, etc.). This allows for more accurate tracking using the observation image and the aiming light image.

The target position may also be automatically detected by estimating the position to be irradiated (such as a dark area different from blood vessels in the case of a microaneurysm) from the luminance information of the entire fundus obtained by the observation optical system 40 and scanning the aiming light. For example, the control unit 60 may estimate the area where the luminance of the return light changes using the luminance distribution of the entire fundus from the observation image, and automatically change the irradiating position.

Reference Signs List 1 Ophthalmic laser treatment device 10 Irradiation optical system 11 Laser light source 17 Deflection unit 18 Objective lens 20 Focus adjustment unit 30 Aiming light receiving optical system 40 Observation optical system 60 Control unit

Claims (7)

An ophthalmic laser treatment device for treating a patient's eye, comprising:
an irradiation means for irradiating the patient's eye with a treatment or targeting laser light;
an adjustment means for adjusting an irradiation position of the laser light;
an observation optical system for photographing the patient's eye to obtain an observation image;
a detection unit that detects a positional deviation of the irradiation position in a direction perpendicular to an optical axis of the laser light based on a reference image serving as a reference for aligning the irradiation position with respect to the patient's eye and the observation image;
a control unit that controls the adjustment unit and corrects the irradiation position based on the position deviation detected by the detection unit,
2. An ophthalmic laser treatment apparatus according to claim 1, wherein said control means updates said reference image based on said observed image. The ophthalmic laser treatment device according to claim 1, characterized in that the control means updates the reference image with the observation image captured after irradiation with the laser light. The ophthalmic laser treatment device according to claim 2, characterized in that the detection means detects the positional deviation based on the positions of the coagulation spots shown in the reference image and the observation image updated after the irradiation of the laser light. The ophthalmic laser treatment device of claim 1, characterized in that the detection means detects the positional deviation of the irradiation position in a direction perpendicular to the optical axis of the laser light based on a change in luminance of the image of the aiming light reflected in the observation image. An ophthalmic laser treatment device for treating a patient's eye, comprising:
an irradiation means for irradiating the patient's eye with a laser beam for treatment or aiming;
an adjustment means for adjusting an irradiation position of the laser light;
an aiming light receiving means for receiving return light of the aiming light reflected by the patient's eye;
a detection means for detecting a positional deviation of the irradiation position in a direction perpendicular to the optical axis of the laser light based on a change in luminance of the return light received by the aiming light receiving means;
a control means for controlling the adjustment means and correcting the irradiation position based on the position deviation detected by the detection means. An ophthalmic laser treatment program executed in an ophthalmic laser treatment apparatus for treating a patient's eye, the program being executed by a control means of the ophthalmic laser treatment apparatus,
an irradiation step of irradiating the patient's eye with a treatment or targeting laser light;
an adjusting step of adjusting an irradiation position of the laser light;
an image acquiring step of acquiring an observation image by photographing the patient's eye;
a detection step of detecting a positional deviation of the irradiation position in a direction perpendicular to an optical axis of the laser light based on a reference image serving as a reference for aligning the irradiation position with respect to the patient's eye and the observation image;
a correction step of correcting the irradiation position based on the positional deviation detected in the detection step;
updating the reference image with the observed image;
4. An ophthalmic laser treatment program for causing the ophthalmic laser treatment apparatus to execute the above steps. An ophthalmic laser treatment program executed in an ophthalmic laser treatment apparatus for treating a patient's eye, the program being executed by a control means of the ophthalmic laser treatment apparatus,
an irradiation step of irradiating the patient's eye with a treatment or targeting laser light;
an adjusting step of adjusting an irradiation position of the laser light;
an aiming light receiving step of receiving return light of the aiming light reflected by the patient's eye;
a detection step of detecting a positional deviation of the irradiation position in a direction perpendicular to the optical axis of the laser light based on a change in luminance of the return light received in the aiming light receiving step;
a correction step of correcting the irradiation position based on the positional deviation detected in the detection step;
4. An ophthalmic laser treatment program for causing the ophthalmic laser treatment apparatus to execute the above steps.