Patent Publication Number: US-2023148861-A1

Title: Optical system and operating method thereof

Description:
BACKGROUND OF THE INVENTION 
     1. Field of the Invention 
     The invention relates to an optical system; in particular, to an optical system and an operating metho thereof applied to eyes. 
     2. Description of the Prior Art 
     Low-intensity laser light therapy is a method of treating eye diseases, such as macular degeneration, primary open-angle glaucoma or retinitis pigmentosa. By irradiating the eyes with hand-held or fixed low-intensity infrared lasers (670 nm or 780 nm, 10 mW or less), the blood vessels of the eyes can be dilated, and the blood circulation of the retina and choroid tissue can be improved, thereby reducing the symptoms of ocular tissue hypoxia and ischemia caused by glaucoma, macular and retinopathy. 
     Furthermore, low-intensity laser illumination can also reduce the generation of ocular fluid and enhance the efficiency of fluid discharge, thereby reducing intraocular pressure, thereby reducing glaucoma symptoms. In addition, mitochondrial dysfunction is considered to be a main pathological factor of glaucoma. Some papers have pointed out that irradiating eye cells with low-intensity lasers can stimulate mitochondria to synthesize adenosine triphosphate (ATP) to increase mitochondrial function, thereby improving glaucoma symptoms. 
     However, since the eyes naturally vibrate, it greatly increases the difficulty of locking a specific position, so that the conventional light therapy can only roughly illuminate a large area of the fundus instead of scanning or locking detailed areas of the fundus for intensive treatment. In addition, the therapeutic effect after phototherapy still needs to be determined by taking a fundus image of the area with other instruments, which is quite time-consuming and inconvenient. 
     Therefore, the above-mentioned problems encountered in the prior art still need to be further solved. 
     SUMMARY OF THE INVENTION 
     Therefore, the invention provides an optical system and an operating method thereof applied to eyes to solve the above-mentioned problems of the prior arts. 
     A preferred embodiment of the invention is an optical system. In this embodiment, the optical system includes a light source device, a gaze module and a fundus detection device. The light source device includes a light source module, a light intensity modulation module and a lens module. The light source module is used to emit a therapy light to an eye. The light intensity modulation module is used to modulate an intensity of the therapy light. The lens module is used to control a depth of the therapy light. The gaze module is used to be gazed by the eye to fix a fundus of the eye. The fundus detection device and the light source device are integrated to detect the fundus to obtain a fundus image. 
     In an embodiment, when the light source module only includes a single light source, the single light source needs to be matched with a light scanning module to modulate the therapy light to irradiate to a specific position and range of the eye. 
     In an embodiment, when the light source module includes a plurality of light sources arranged in an array, the plurality of light sources can operate independently and only provide light therapy of a rough position and range. 
     In an embodiment, the fundus detection device is a fundus camera or an optical coherence tomography scanner. 
     In an embodiment, the optical system further includes a switch module coupled to the light source device, the switch module selectively turns on the light source device according to whether a specific area of the eye is scanned by the light scanning module, so as to track the specific position of the eye and shoot its image to avoid the effects of natural shaking of the eye. 
     In an embodiment, the optical system further includes an irradiation position control optical path and an irradiation range control lens configured to lock a specific area of the eye to be irradiated and shoot its image to avoid the effects of the natural shaking of the eye. 
     In an embodiment, the optical system further includes an analysis module and a feedback control module of the light scanning module configured to correct and synchronize coordinates of the optical coherence tomograph and coordinates of the light scanning module. 
     In an embodiment, the light intensity modulation module modulates the luminous intensity of the light source module correspondingly according to the thickness of each retinal layer of the eye analyzed by the optical coherence tomography scanner, so as to precisely control the dose of light therapy. 
     In an embodiment, the lens module controls the convergence and divergence of the therapy light according to the thickness of each retinal layer of the eye analyzed by the optical coherence tomography scanner, so as to precisely control the depth of light treatment. 
     Another preferred embodiment of the invention is an optical system operating method. In this embodiment, the optical system operating method includes steps of: (a) disposing a gaze module for an eye to gaze to fix a fundus of the eye; (b) emitting a therapy light to an eye; (c) modulating an intensity of the therapy light and controlling a depth of the therapy light; and (d) detecting the fundus to obtain a fundus image. 
     In an embodiment, when the light source module only comprises a single light source, the single light source needs to be matched with a light scanning module to modulate the therapy light to irradiate to a specific position and range of the eye. 
     In an embodiment, the step (b) is to emit the therapy light through a plurality of light sources arranged in an array, and the plurality of light sources can operate independently and only provide light therapy of a rough position and range. 
     In an embodiment, the step (b) is performed by a fundus camera or an optical coherence tomography scanner. 
     In an embodiment, the optical system operating method further includes a step of: selectively turning on the single light source according to whether a specific area of the eye is scanned by the light scanning module, so as to track a specific position of the eye and shoot its image to avoid the effects of natural shaking of the eye. 
     In an embodiment, the optical system operating method further includes a step of: disposing an irradiation position control optical path and an irradiation range control lens to lock a specific area of the eye to be irradiated and shoot its image to avoid the effects of the natural shaking of the eye. 
     In an embodiment, the optical system operating method further includes a step of: disposing an analysis module and a feedback control module of the light scanning module to correct and synchronize coordinates of the optical coherence tomograph and coordinates of the light scanning module. 
     In an embodiment, the optical system operating method further includes a step of: modulating the luminous intensity of the light source module correspondingly according to the thickness of each retinal layer of the eye analyzed by the optical coherence tomography scanner, so as to precisely control the dose of light therapy. 
     In an embodiment, the optical system operating method further includes a step of: controlling the convergence and divergence of the therapy light according to the thickness of each retinal layer of the eye analyzed by the optical coherence tomography scanner, so as to precisely control the depth of light treatment. 
     Compared to the prior art, the optical system and its operating method of the invention can scan the local area of the fundus, avoid the influence of natural eye shaking to lock the local position, make the low-intensity light source focus on the specific area and depth, and analyze the thickness of the target tissue layer of the retina by optical coherence tomography technology to adjust the appropriate light dose, and take pictures of the eye area before and after treatment to follow up the treatment effect, which effectively solves the problems that conventional phototherapy instruments can only roughly irradiate the entire eye, and unable to focus on localized areas of the eye or target delicate areas, unable to control the light dose according to the thickness of the tissue, and unable to directly use the same instrument to observe the treatment effect after the treatment is completed, so it can achieve five-dimensional (three-dimensional space, time, light dose) light treatment effect and the different retinal layers can also be treated with lights of different wavelengths. 
     The advantage and spirit of the invention may be understood by the following detailed descriptions together with the appended drawings. 
    
    
     
       BRIEF DESCRIPTION OF THE APPENDED DRAWINGS 
         FIG.  1    illustrates a schematic diagram of the optical system in an embodiment of the invention. 
         FIG.  2    illustrates a timing diagram that when the therapy light and the illumination light share the same light source, the brightness of the light source is rapidly switched in the same treatment cycle to achieve effects of treatment and imaging lighting. 
         FIG.  3    illustrates a flowchart of the optical system operating method in another embodiment of the invention. 
         FIG.  4    illustrates an optical path schematic diagram of the light therapy light source, gaze module, optical path coupling module and the eye to be tested. 
         FIG.  5    illustrates a schematic diagram that the therapy light source and the optical path coupling module can be manually/automatically adjusted by mechanical linkage when combined with a wearable device. 
         FIG.  6    illustrates a schematic diagram of the optical system in another embodiment of the invention. 
         FIG.  7    illustrates a flowchart of the optical system operating method in another embodiment of the invention. 
         FIG.  8    illustrates an optical path schematic diagram that the detection light source and the light therapy light source share the scanning module. 
         FIG.  9 A  illustrates an optical path schematic diagram that the detection light source and the light therapy light source do not share the scanning module. 
         FIG.  9 B  illustrates an optical path schematic diagram of using the photosensitive module to perform position correction on the detection light beam scanning module and the therapy light beam scanning module. 
         FIG.  10    illustrates a schematic diagram of the range of light spots scanned by the detection light and the therapy light on the photosensitive module. 
         FIG.  11    illustrates a flowchart of the optical system operating method correcting the light scanning module for detection the detection light and the therapy light in another embodiment of the invention. 
         FIG.  12    illustrates a block diagram of a light therapy light source. 
     
    
    
     DETAILED DESCRIPTION OF THE INVENTION 
     Exemplary embodiments of the invention are referenced in detail now, and examples of the exemplary embodiments are illustrated in the drawings. Further, the same or similar reference numerals of the components in the drawings and the detailed description of the invention are used on behalf of the same or similar parts. 
     The invention provides an optical system related to the treatment of eye diseases and an operating method thereof, which can integrate a phototherapy device using photodynamic therapy and low-level laser therapy and a fundus detection optical path (fundus camera, optical coherence tomography) to achieve specific area or precise position-locked irradiation, control the light dose, capture fundus images and structural data after phototherapy, so as to track the treatment effect and effectively solve the problems encountered by the previous technology. 
     A preferred embodiment of the invention is an optical system. In this embodiment, the optical system includes a light source device, a gaze module and a fundus detection device. The light source device includes a light source module, a light intensity modulation module and a lens module. The light source module is used to emit a therapy light to an eye. The light intensity modulation module is used to modulate an intensity of the therapy light. The lens module is used to control a depth of the therapy light. The gaze module is used to be gazed by the eye to fix a fundus of the eye. The fundus detection device and the light source device are integrated to detect the fundus to obtain a fundus image. 
     In fact, the fundus detection device can be a fundus camera or an optical coherence tomography scanner, but not limited to this. The light intensity modulation module can modulate the luminous intensity of the light source module correspondingly according to the thickness of each retinal layer of the eye analyzed by the optical coherence tomography scanner, so as to precisely control the dose of light therapy, but not limited to this. 
     In fact, the light source module can only include a single light source or a plurality of light sources arranged in an array. When the light source module only includes a single light source, the single light source needs to be matched with a light scanning module to modulate the therapy light to irradiate to a specific position and range of the eye. When the light source module includes a plurality of light sources arranged in an array, the plurality of light sources can operate independently and only provide light therapy of a rough position and range. 
     In another embodiment, the optical system can further include a switch module. The switch module is coupled to the light source device. The switch module can selectively turn on the light source device according to whether a specific area of the eye is scanned by the light scanning module, so as to track the specific position of the eye and shoot its image to avoid the effects of natural shaking of the eye. 
     In another embodiment, the optical system can further include an irradiation position control optical path and an irradiation range control lens configured to lock a specific area of the eye to be irradiated and shoot its image to avoid the effects of the natural shaking of the eye, but not limited to this. 
     In another embodiment, the optical system can further include an analysis module and a feedback control module of the light scanning module configured to correct and synchronize coordinates of the optical coherence tomograph and coordinates of the light scanning module, but not limited to this. 
     Please refer to  FIG.  1   .  FIG.  1    illustrates a schematic diagram of an optical system according to an embodiment of the invention. As shown in  FIG.  1   , the optical system  1  includes an illumination module  10 , a gaze module  12 , an imaging module  14 , a light therapy light source  16  and an optical path coupling module  18 . The illumination module  10 , the gaze module  12  and the light therapy light source  16  are respectively coupled to the light path coupling module  18 . The optical path coupling module  18  is coupled to the imaging module  14 . The gaze module  12  is used for the eye E to be tested to watch, so that the orientation of the fundus of the eye E to be tested can be fixed. The light therapy light source  16  provides a therapy light L 2  to the light path coupling module  18  and the light path coupling module  18  emits the therapy light L 2  to the fundus of the eye E to be tested for light therapy. The illumination module  10  provides an illumination light L 1  to the light path coupling module  18  and the light path coupling module  18  emits the illumination light L 1  to the fundus of the eye E to be tested. The fundus of the eye E to be tested reflects the illumination light L 1  to form a reflected light RL and the reflected light RL is emitted to the imaging module  14  through the optical path coupling module  18 , so that the imaging module  14  can capture the fundus image of the eye E to be tested. 
     Please refer to  FIG.  2   . It is assumed that the illumination light L 1  and the therapy light L 2  are provided by the same light source (such as infrared light), the light source can be quickly switched to provide the illumination light L 1  with higher brightness or the therapy light L 2  with lower brightness at different working times in the same treatment period T, so that the illumination light L 1  and the therapy light L 2  can be provided at different working times respectively, so it can have both therapy and imaging lighting effects. 
     Please refer to  FIG.  3   .  FIG.  3    illustrates a flowchart of the optical system operating method in another embodiment of the invention. As shown in  FIG.  3   , the optical system operating method can include the following steps: 
     Step S 10 : the eye E to be tested watching the gaze module  12  to fix the orientation of the fundus of the eye E to be tested; 
     Step S 12 : the light therapy light source  16  emitting the therapy light L 2  to the eye E to be tested; 
     Step S 14 : turning off the light therapy light source  16 ; 
     Step S 16 : turning on the illumination module  10  to emit the illumination light L 1  to illuminate the fundus of the eye E to be tested; and 
     Step S 18 : the imaging module  14  capturing the fundus image of the eye E to be tested. 
     For example, when the light source of the gaze module  12  is turned on, the subject&#39;s eye E to be tested watches the light source of the gaze module  12  to fix the orientation of the fundus of the eye E to be tested. Next, turning on single or multiple light sources in the light therapy light source  16  and moving one or more lenses or mirrors in the optical path coupling module  18  to adjust the range and position of the therapy light L 2  emitted by the light therapy light source  16  to the fundus of the eye E to be tested. After the course of the light therapy is over, before the fundus image is captured, if the imaging module  14  does not include a filter for the wavelength used by the light therapy light source  16 , the light therapy light source  16  is turned off. Next, the illumination module  10  is turned on to emit the illumination light L 1  to the fundus of the eye E to be tested, and the imaging module  14  captures the fundus image of the eye E to be tested. 
     Please refer to  FIG.  4   .  FIG.  4    illustrates a schematic diagram of the light path of the light therapy light source  16 , the gaze module  12 , the light path coupling module  18  and the eye E to be tested. 
     As shown in  FIG.  4   , the gaze module  12  includes a light source  120  and a lens LEN that can move up and down. The light therapy light source  16  includes a light source  160  and a lens LEN that can move left and right, which is used for the eye E to be tested to watch, so as to fix the orientation of the fundus of the eye E to be tested. The therapy light L 2  emitted by the light source  160  is refracted by the lens LEN and then emitted to the eye E to be tested through the optical path coupling module  18  to perform light therapy. 
     It should be noted that,  FIG.  4    is the common optical path design of fundus camera: the therapy light L 2  emitted by the point light source  160  of the light therapy light source  16  is converged on the pupil plane of the eye E to be tested through the optical path coupling module  18 , and then diffusely irradiated to the fundus of the eye E to be tested. The light path coupling module  18  can be composed of a plurality of lenses, lens arrays and mirrors, so as to achieve the effect of individually controlling the range and position of the light therapy light source  16  irradiating the fundus. The light path between the light therapy light source  16 , the light path coupling module  18  and the eye E to be tested is not limited to this. The light sources  120  of the gaze module  12  are respectively disposed at different positions, and the light sources  120  at different positions can be lit up for the eye E to watch and the angle of the eye E to be tested can be adjusted accordingly. 
     Please refer to  FIG.  5   , when the optical system of the invention is combined with the wearable device, the light therapy light source  16  and the optical path coupling module  18  can be manually/automatically adjusted by mechanical linkage, and the light therapy light source  16  can also be controlled by DLP technology. The therapy light L 2  emitted from the light therapy light source  16  is projected onto the area of the fundus of the eye E to be tested. 
     Please refer to  FIG.  6   .  FIG.  6    illustrates a schematic diagram of the optical system in another embodiment of the invention. As shown in  FIG.  6   , the optical system  6  includes a light source  60 , a reference optical path modulation module  61 , a gaze module  62 , an analysis system  64 , a light therapy light source  66 , an optical path coupling module  68  and a light scanning module  69 . The light source  60 , the reference light optical path modulation module  61 , the gaze module  62 , the analysis system  64 , the light therapy light source  66  and the light scanning module  69  are all coupled to the optical path coupling module  68 . The analysis system  64  is respectively coupled to the light therapy light source  66 , the light path coupling module  68  and the light scanning module  69 . The light scanning module  69  is disposed between the light path coupling module  68  and the eye E to be tested. 
     The light source  60  provides a light L required for optical coherence tomography, and when the light L enters the optical path coupling module  68 , it is divided into a detection light LD and a reference light LR. The detection light LD enters the light scanning module  69  and is guided to a specific position of the eye E to be tested, and then is reflected back to the light path coupling module  68 . The reference light LR enters the reference light optical path modulation module  61  to adjust the optical path and is reflected back to the optical path coupling module  68 . The reflected detection light LD′ and the reflected reference light LR′ are interfered and analyzed by the analysis system  64  to obtain the fundus structure of the specific position of the eye E to be tested. 
     The gaze module  62  provides a target for the eye E to watch, and the gaze module  62  can be formed by an LCD panel or a plurality of LEDs. By modulating the different positions of the gaze light spot, the gaze angle of the eye E to be tested is changed, so as to facilitate the detection light LD and the therapy light L 2  are emitted to the selected area of the eye E to be tested. The analysis system  64  records and analyzes the current scanning site and the to-be-scanned site. When the selected area is about to be scanned, the light therapy light source  66  is turned on. When leaving the selected area, the light therapy light source  66  is turned off. 
     In addition, the analysis system  64  can control the light scanning module  69  to lock the scanning area. The detection light LD and the therapy light L 2  may or may not share the light scanning module  69 . If the light scanning module  69  is shared, the light therapy light source  66  needs to be turned off/on when the scanning position leaves/enters the selected area. If the light scanning module  69  is not shared, the detection light LD scans the fundus of the eye E to be tested to confirm the movement of the fundus and track the selected area, and the light therapy light source  66  can use the independent light scanning module  69  to continuously illuminate the selected area. And, the independent light scanning module  69  can add a lens to adjust the irradiation range of the light therapy light source  66 . 
     Please refer to  FIG.  7   .  FIG.  7    illustrates a flowchart of the optical system operating method in another embodiment of the invention. As shown in  FIG.  7   , the optical system operating method can include the following steps: 
     Step S 70 : the eye E to be tested watches the gaze module  62  to fix the orientation of the fundus of the eye E to be tested; 
     Step S 71 : the light emitted by the light source  60  is divided into the reference light LR and the detection light LD through the optical path coupling module  68 . The reference light LR enters the reference light optical path modulation module  61  to adjust the optical path and is reflected back to the optical path coupling module  68 . The detection light LD enters the fundus of the eye E to be tested and is reflected back to the optical path coupling module  68 . The reflected probe light LD′ and the reflected reference light LR′ are interfered with, captured and analyzed by the analysis system  64 ; 
     Step S 72 : the light scanning module  69  modulates the position of the detection light LD; 
     Step S 73 : determining whether the scanning analysis of the specific area of the fundus is completed; 
     Step S 74 : if the determination result of the step S 73  is yes, capturing or matching the specific area features in the analysis system  64  to lock the phototherapy area; 
     If the determination result of the step S 73  is no, then return to the step S 71 ; 
     Step S 75 : determining whether the match is a phototherapy area; 
     Step S 76 : if the determination result of the step S 75  is yes, turning on the light therapy light source; 
     Step S 77 : if the determination result of the step S 75  is no, turning off the light therapy light source; 
     Step S 78 : determining whether the phototherapy is completed; 
     Step S 79 : if the determination result of the step S 78  is yes, turning off the light source and the light therapy light source; and 
     If the determination result of step S 78  is no, then go back to step S 71 . 
     For example, when the light source of the gaze module  62  is turned on, the subject&#39;s eye E to be tested watches the light source of the gaze module  62  to fix the orientation of the fundus of the eye E to be tested. Next, the optical coherence tomography of the fundus was started and the characteristics of the fundus were analyzed. When the analysis system  64  selects the area to be locked, the analysis system  64  continuously detects the movement direction of the area, changes the position scanned by the light scanning module  69  to perform area locking. When the scanning position leaves/enters the selected area, the light therapy light source needs to be turned off/on. In addition, because the optical coherence tomography can obtain the blood vessel distribution map of the fundus, it can be used as the identification of individual retinal characteristics. During the scanning process, the analysis system can go to the database to extract the historical scanning records of the subjects, track the historical treatment site and curative effect, and analyze whether there are new features (possibly new symptoms). 
     Please refer to  FIG.  8   .  FIG.  8    illustrates a schematic diagram of the optical path when the detection light source  60  and the light therapy light source  66  share the same detection light beam scanning module  69 . As shown in  FIG.  8   , a switch  63  is added to the optical coherence tomography optical path. When the system scans the local area of the eye E to be tested, the light therapy light source  66  is turned on, and when the system leaves the local area of the eye E to be tested, the light therapy light source  66  is turned off. Thereby, the effect of treating and improving the disease of the part of the eye E to be tested can be achieved when scanning the local area of the eye E to be tested. 
     Please refer to  FIG.  9 A .  FIG.  9 A  illustrates a schematic diagram of the light path when the detection light source  60  and the light therapy light source  66  do not share the scanning module  69 . As shown in  FIG.  9 A , a therapy light scanning module  67  is added to the optical path of optical coherence tomography, so that the effects of using the detection light scanning module  69  to scan the local area of the eye E to be tested and using the therapy light scanning module  67  to treat diseases in another local area of the eye E to be tested can be achieved. 
     Please refer to  FIG.  9 B  and  FIG.  10   .  FIG.  9 B  illustrates a schematic diagram of the optical path required for position correction of the detection light scanning module  69  and the therapy light scanning module  67  using the photosensitive module  68 .  FIG.  10    illustrates a schematic diagram of the range of light spots scanned by the detection light and the therapy light on the photosensitive module  68 , which can be used to correct the positions of the detection light scanning module  69  and the therapy light scanning module  67 . 
     In practical applications, before starting to use the eye E to be tested, it is necessary to perform calibration of the control position range of the detection light scanning module  69  and the therapy light scanning module  67 , so that the detection light and the therapy light can be adjusted. Different areas within the eye E to be tested are scanned separately. 
     For example, the calibration method can include the following steps: using the photosensitive module  68  to detect the detection light and the therapy light; after leaving a series of light spot ranges, we can know the coordinates of the moving range of the detection light scanning module  69 . Afterwards, the therapy light scanning module  67  is used to move the therapy light, and another series of light spot ranges can be left in the field of view of the photosensitive module  68 , so that the coordinates of the moving range of the therapy light scanning module  67  can be known. Finally, these two sets of coordinates are aligned to complete the calibration. 
     Please refer to  FIG.  11   .  FIG.  11    illustrates a flowchart of the optical system operating method for calibrating the light scanning module of the detection light/therapy light according to another embodiment of the invention. As shown in  FIG.  11   , the optical system operating method can include the following steps: 
     Step S 110 : the photosensitive module  68  that can detect the detection light and the therapy light is disposed in the optical path, and is ready to start calibration; 
     Step S 112 : moving the detection light with the detection light scanning module  69 , scanning a series of light spots on the photosensitive module  68  in sequence, and recording the coordinates of the detection light scanning range; 
     Step S 114 : using the therapy light scanning module  67  to move the therapy light, scanning a series of light spots on the photosensitive module  68  in sequence, and recording the coordinates of the therapy light scanning range; 
     Step S 116 : recording the coordinates of the scanning range of the detection light and the coordinates of the scanning range of the therapy light and aligning the two to complete the calibration; and 
     Step S 118 : the therapy light scanning module  67  can move independently of the detection light scanning module  69  to treat a specific position within the visual field of the eye E to be tested. 
     It should be noted that, in order to make the therapy light energy move independently of the detection light during treatment, it is necessary to use the photosensitive module  68  to measure the coordinates of the spot movement range of the detection light scanning module  69 , and then measure t the coordinates of the moving range of the light spot of the therapy light scanning module  67 , and finally align the two sets of coordinates to complete the calibration. In this way, the corrected therapy light scanning module  67  can move independently of the detection light scanning module  69  to treat diseases at a specific position within the visual field of the eye E to be tested. 
     Referring to  FIG.  12   , in one embodiment, the light therapy light source  66  can include a light source  660 , a light intensity modulation module  662  and a lens module  664 . The light source  660  can be a single light source or an array of light sources. The light intensity modulation module  662  can change the intensity of the therapy light entering the lens module  664  by means of liquid crystal or adjusting the polarization of the light source. The lens module  664  can adjust the contraction and divergence of the therapy light, and provide another degree of freedom to control the irradiation range of the fundus irradiated on the eye E to be tested. 
     Compared to the prior art, the optical system and its operating method of the invention can scan the local area of the fundus, avoid the influence of natural eye shaking to lock the local position, make the low-intensity light source focus on the specific area and depth, and analyze the thickness of the target tissue layer of the retina by optical coherence tomography technology to adjust the appropriate light dose, and take pictures of the eye area before and after treatment to follow up the treatment effect, which effectively solves the problems that conventional phototherapy instruments can only roughly irradiate the entire eye, and unable to focus on localized areas of the eye or target delicate areas, unable to control the light dose according to the thickness of the tissue, and unable to directly use the same instrument to observe the treatment effect after the treatment is completed, so it can achieve five-dimensional (three-dimensional space, time, light dose) light treatment effect and the different retinal layers can also be treated with lights of different wavelengths. 
     With the example and explanations above, the features and spirits of the invention will be hopefully well described. Those skilled in the art will readily observe that numerous modifications and alterations of the device may be made while retaining the teaching of the invention. Accordingly, the above disclosure should be construed as limited only by the metes and bounds of the appended claims.