WO2024034658A1 - コンタクトレンズ型眼内照明機器 - Google Patents

コンタクトレンズ型眼内照明機器 Download PDF

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Publication number
WO2024034658A1
WO2024034658A1 PCT/JP2023/029230 JP2023029230W WO2024034658A1 WO 2024034658 A1 WO2024034658 A1 WO 2024034658A1 JP 2023029230 W JP2023029230 W JP 2023029230W WO 2024034658 A1 WO2024034658 A1 WO 2024034658A1
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WIPO (PCT)
Prior art keywords
contact lens
region
light
illumination device
light source
Prior art date
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PCT/JP2023/029230
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English (en)
French (fr)
Japanese (ja)
Inventor
翔平 森川
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University of Tsukuba NUC
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University of Tsukuba NUC
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Priority to JP2024540521A priority Critical patent/JPWO2024034658A1/ja
Priority to EP23852620.6A priority patent/EP4574107A1/en
Publication of WO2024034658A1 publication Critical patent/WO2024034658A1/ja
Anticipated expiration legal-status Critical
Ceased legal-status Critical Current

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    • G—PHYSICS
    • G02—OPTICS
    • G02C—SPECTACLES; SUNGLASSES OR GOGGLES INSOFAR AS THEY HAVE THE SAME FEATURES AS SPECTACLES; CONTACT LENSES
    • G02C7/00—Optical parts
    • G02C7/02—Lenses; Lens systems ; Methods of designing lenses
    • G02C7/04—Contact lenses for the eyes
    • G—PHYSICS
    • G02—OPTICS
    • G02C—SPECTACLES; SUNGLASSES OR GOGGLES INSOFAR AS THEY HAVE THE SAME FEATURES AS SPECTACLES; CONTACT LENSES
    • G02C11/00—Non-optical adjuncts; Attachment thereof
    • G02C11/04—Illuminating means

Definitions

  • the present invention relates to a contact lens type intraocular illumination device.
  • This application claims priority based on Japanese Patent Application No. 2022-128395 filed in Japan on August 10, 2022, the contents of which are incorporated herein.
  • Eye diseases such as cataracts, retinal detachment, age-related macular degeneration, and diabetic retinopathy are known as causes of visual impairment, and these eye diseases are also causes of blindness. It is considered desirable to prevent eye diseases from progressing through early diagnosis.
  • cataracts are diagnosed by examining the transparency of the lens using a slit lamp microscope and can be treated with surgery.
  • Retinal detachment is diagnosed by fundus examination and treated with vitrectomy or intrascleral surgery.
  • Age-related macular degeneration is diagnosed by fundus examination, and treatments include photodynamic therapy.
  • Diabetic retinopathy is diagnosed by retinal photography and can be treated by laser photocoagulation, vitrectomy, etc. Diabetic retinopathy often has no early warning symptoms, but defect abnormalities such as microaneurysms, retinal hemorrhages, beaded dilatation of retinal veins, and other microdefect abnormalities appear on retinal photographs.
  • a port is formed in the sclera at a position approximately 3.5 mm to 4.0 mm from the corneal contour, and the intraocular illumination device is inserted into the eye through the port (for example, Patent Document 1) .
  • Photodynamic therapy known as a treatment for macular degeneration, involves the use of wirelessly powered smart contact lenses equipped with a drug reservoir containing a photosensitizing agent, a photodetector, and micro-LEDs or OLEDs.
  • a signal from a photodetector first releases a photosensitizing agent stored in a drug reservoir through the system and transmits it to the retinal defect.
  • the photosensitizer a material that reacts with light and produces active oxygen is used.
  • micro-LED or OLED light is used to create active oxygen, which is then used to treat macular degeneration.
  • a contact lens assembly includes a contact lens including a proximal curved surface disposed near the eye and a distal flat surface opposite the proximal curved surface, and a distal flat surface of the contact lens.
  • a light source having an annular shape in a plan view, which is provided at a position outside the curved surface on the proximal side of the surface and connected to an external light source through an optical fiber, and a cylindrical reflector provided so as to surround the light source. , and a camera provided on the distal curved surface of the contact lens.
  • a retinal photograph is taken by irradiating light from a light source provided outside the contact lens toward the proximal curved surface.
  • the intraocular illumination device When using an invasive intraocular illumination device like the one disclosed in Patent Document 1, the intraocular illumination device is inserted into the eye through a port, so even if sterilization is performed appropriately, there is no residue left in the intraocular illumination device. There is a risk of infection due to trace amounts of bacteria and viruses. Furthermore, when using the intraocular illumination device described in Patent Document 1, it is difficult to perform treatment because it is necessary to operate the intraocular illumination device with one hand and perform intraocular treatment with the other hand.
  • a contact lens assembly such as that disclosed in Patent Document 3 is effective for taking retinal photographs, but because it has a special shape and structure, it is not intended to be used for intraocular surgery and is not suitable. do not have. Specifically, a light source and a reflector provided outside the contact lens cannot follow the movements of the eye, and there is a risk of damaging the eyelids and the like. Therefore, it is not suitable for long-term use such as in internal eye surgery. Furthermore, the light source is provided outside the contact lens, making it difficult to illuminate the entire retina.
  • the present invention has been made in view of the above circumstances, and aims to provide a highly versatile contact lens type intraocular illumination device that is suitable for dual-method intraocular surgery while minimizing the risk of infection. shall be.
  • a contact lens type intraocular illumination device includes a dome-shaped first region that is provided in the center and through which light passes, and that extends radially outward from the outer periphery of the first region. a ring-shaped second region extending radially outward from the outer circumferential portion of the second region and provided in contact with the sclera; An irradiation unit is provided in the second region of the contact lens and adjusts refraction or diffusion of light supplied from a light source to irradiate light into the eye.
  • the irradiation unit includes a holographic lens that refracts the light supplied from the light source and guides it into the eye, and an electrical connection with the holographic lens.
  • the holographic lens driving circuit may be connected to the holographic lens driving circuit and change the direction of the holographic lens.
  • the irradiation unit has a plurality of holographic lens units each including the holographic lens and the holographic lens drive circuit.
  • the plurality of holographic lens units may be arranged side by side on the same circumference of the contact lens in a plan view of the contact lens.
  • the plurality of holographic lens units are rotated about the center of a circle of the contact lens in a plan view of the contact lens. They may be arranged symmetrically.
  • the contact lens type intraocular illumination device may further include a light source driving circuit provided in the second region and driving the light source.
  • the irradiation unit includes a light guide plate that guides light supplied from the light source to a diffusion sheet, and a light guide plate laminated on the light guide plate. and a diffusion sheet that diffuses the light from the light guide plate and guides it into the eye.
  • the irradiation unit has a plurality of optical laminated units each including the light guide plate and the diffusion sheet, and the plurality of optical laminated units are , the contact lenses may be arranged side by side on the same circumference of the contact lens in a plan view of the contact lens.
  • the plurality of optical laminated units may be arranged rotationally symmetrically with respect to the center of a circle of the contact lens in a plan view of the contact lens. .
  • the contact lens type intraocular illumination device according to any one of (1) to (8) above, further comprising an anti-reflection film provided on a surface opposite to the wearing surface of the contact lens, The film may be disposed to cover the irradiation unit in a plan view of the contact lens.
  • the thickness of the first region may be 0.15 mm or more and less than 0.25 mm.
  • the contact lens may be a scleral lens with a diameter of 13 mm or more.
  • the light source is provided in the second region, and the light source is provided from outside the contact lens type intraocular lighting device. may be supplied with power.
  • the outer surface of the contact lens opposite to the mounting surface includes a spherical surface corresponding to the first region and a spherical surface corresponding to the second region. It may have a first ring surface that corresponds to the region and is a continuous surface with the spherical surface, and a second ring surface that corresponds to the third region.
  • a contact lens type intraocular illumination device includes a ring-shaped third region provided so as to be in contact with the sclera, and a ring-shaped third region extending radially inward from an inner peripheral portion of the third region. a ring-shaped second region of the contact lens; and an irradiation device provided in the second region of the contact lens that adjusts refraction or diffusion of light supplied from a light source and irradiates light into the eye. It is equipped with a unit.
  • the contact lens type intraocular illumination device may have at least one of the configurations (1) to (8) and (10) to (12) above.
  • FIG. 1 is a cross-sectional view showing an example of the configuration of a contact lens type intraocular illumination device according to an embodiment of the present invention.
  • FIG. 2 is a plan view of the contact lens type intraocular illumination device of FIG. 1 viewed from the operator's side (outer peripheral surface side).
  • FIG. 2 is a diagram showing the contact lens type intraocular illumination device of FIG. 1 being attached to a patient's eye.
  • 2 is a sectional view showing a modification of the contact lens type intraocular illumination device of FIG. 1.
  • FIG. FIG. 3 is a cross-sectional view showing an example of the configuration of a contact lens type intraocular illumination device according to another embodiment of the present invention.
  • FIG. 6 is a plan view of the contact lens type intraocular illumination device of FIG.
  • FIG. 6 is a sectional view showing a modification of the contact lens type intraocular illumination device of FIG. 5.
  • FIG. 1 is a sectional view showing an example of the configuration of a contact lens type intraocular illumination device according to an embodiment of the present invention
  • FIG. FIG. 3 is a plan view of the contact lens type intraocular illumination device of FIG. 1 being attached to a patient's eye.
  • light irradiated into the eye is indicated by a two-dot chain line.
  • a cornea 70, a crystalline lens 71, an iris 72, and a sclera 73 are illustrated for convenience of explanation.
  • a contact lens type intraocular illumination device 100A shown in FIGS. 1 to 3 includes a dome-shaped first region 1 that is provided in the center and through which light passes, and that extends radially outward from the outer periphery of the first region 1.
  • a contact lens 10 including a ring-shaped second region 2 , and a ring-shaped third region 3 extending radially outward from the outer periphery of the second region 2 and being in contact with the sclera 73 . and an irradiation unit 4A that is provided in the second region 2 of the contact lens 10 and adjusts the refraction of the light supplied from the light source to irradiate the light into the eye.
  • the central portion means near the center in plan view and not located at the edge.
  • the central portion is surrounded by other areas.
  • the outer periphery means a region spaced radially outward from the center in plan view, and the outer periphery of the first region 1 is the region closest to the second region 2 among the first regions 1.
  • the outer peripheral portion of the second region 2 is the portion of the second region 2 that is closest to the third region.
  • the contact lens 10 is a scleral lens that includes a first region 1, a second region 2, and a third region 3 in order from the inside in the radial direction.
  • the first region 1, the second region 2, and the third region 3 are sometimes called an optical zone, a Z-zone, and a landing zone, respectively.
  • the first region 1 is a region for an operator to observe the inside of the eye using, for example, a microscope.
  • the second region 2 is a region where the irradiation unit 4A is formed, and is located between the first region 1 and the third region 3.
  • the third region 3 is a region for attaching the contact lens 10 to the patient's sclera 73.
  • a mounting surface of the third region 3 that is attached to the sclera 73 is designated by the reference numeral 3A.
  • the surface opposite to the wearing surface 3A is referred to as an outer surface.
  • the outer surface of the contact lens 10 includes, for example, a spherical surface corresponding to the first region 1, a first ring surface corresponding to the second region 2 and continuous with the spherical surface, and a first ring surface corresponding to the third region 3. It has a first ring surface and a second ring surface that is a continuous surface.
  • the spherical surface is the surface on the outside (S1) side of the first region 1
  • the first ring surface is the surface on the outside (S1) side of the second region 2
  • the second ring surface is the surface on the outside (S1) side of the third region. This is the (S1) side surface.
  • the diameter (DIA) of the contact lens 10 is, for example, 13 mm or more, and may be 15 mm or more, or 16 mm or more.
  • the above diameter satisfies both the horizontal diameter and the vertical diameter.
  • the first region 1 is, for example, a region including the center of the contact lens 10 in plan view and having a diameter of 3.0 to 6.0 mm.
  • the thickness of the first region 1 may vary depending on the position, but may be, for example, 0.1 mm or more and less than 0.5 mm, 0.15 mm or more and less than 0.25 mm, and 0.15 mm or more and less than 0.25 mm. It may be less than 20 mm. Since the contact lens type intraocular illumination device 100A according to this embodiment is used during surgery, it can be used even if the first region 1 has a thin structure with a thickness of less than 0.25 mm. When the thickness of the first region 1 is as small as 0.25 mm, it is preferable from the viewpoint of preventing obstruction of the observation system in intraocular surgery.
  • the second region 2 is a region located further in the outer circumferential direction than the first region 1, and its size (width) in the radial direction is, for example, 2.0 to 5.0 mm.
  • the second region 2 is a region connected to the first region 1 and the third region 3, and has, for example, an inclined structure with a steeper gradient than the third region 3.
  • the outer periphery of the second region 2 is located, for example, at a distance of 10 to 13 mm from the center of the contact lens 10 in plan view. For example, the thickness of the second region 2 increases as the distance from the center of the circle increases in the radial direction.
  • the thickness of the second region 2 is larger than the thickness of the first region 1, and is preferably 0.3 mm or more and less than 2.0 mm, and preferably 0.3 mm or more and less than 0.75 mm. Since the second region 2 is where the irradiation unit 4A is formed, its thickness is sufficiently large to ensure its strength, and its sufficiently small thickness can suppress the influence on other surgical instruments and observation systems. .
  • the center of the contact lens 10 in plan view may be simply referred to as the circle center.
  • the third region 3 is provided so as to be in contact with the sclera 73.
  • the width of the third region 3 in the radial direction is, for example, 1 to 2 mm.
  • the third region 3 is provided so as to be in contact with the sclera 73 on the mounting surface 3A.
  • the contact lens 10 is made of a material such as glass, methacrylic resin, or acrylic resin.
  • the first region 1, second region 2, and third region 3 that constitute the contact lens 10 are, for example, provided integrally and made of the same material. However, the present invention is not limited to this, and the first region 1, second region 2, and third region 3 may be molded from different materials, and the contact lens 10 may be formed by bonding these.
  • the contact lens type intraocular illumination device 100A further includes an antireflection film 30 on the surface of the contact lens 10 opposite to the mounting surface 3A.
  • the antireflection film 30 is disposed to cover the irradiation unit 4A when the contact lens 10 is viewed from above.
  • the antireflection film 30 has, for example, an annular shape in plan view.
  • the antireflection film 30 is provided to overlap at least the second region 2, and may be provided to overlap the second region 2 and the third region 3.
  • the cross-sectional shape of the antireflection film 30 is, for example, a shape along the surface of the contact lens 10 opposite to the mounting surface 3A.
  • the antireflection film 30 is typically provided in direct contact with the second region 2, but is not limited to this and may be provided via another film.
  • the antireflection film 30 is a film having an antireflection structure, and is, for example, a black filter, a structure in which layers of a high refractive index material and a layer of a low refractive index material are alternately laminated, a film with a moth-eye structure, or the like.
  • the antireflection film 30 plays a role of absorbing light from the outside (S1) of the contact lens type intraocular illumination device 100A, such as a light source provided in a surgical microscope, for example. Further, the antireflection film 30 plays a role of absorbing, for example, light that enters the eye from the light source 52 through the first region 1 and is reflected within the eye (S2).
  • the irradiation unit 4A is provided within the second region 2 of the contact lens 10, for example.
  • the irradiation unit 4A plays the role of illuminating the inside of the patient's eye.
  • the irradiation unit 4A illuminates the inside of the patient's eye so that the central illuminance at the fundus is 10,000 to 100,000 lx.
  • the above illuminance is based on JIS Z9110:2010.
  • the irradiation unit 4A is electrically connected to a holographic lens 21 that refracts light supplied from a light source 52 and guides it into the eye, and a holographic lens drive that changes the direction of the holographic lens 21. It has at least one circuit 22.
  • the holographic lens 21 and the holographic lens drive circuit 22 will be collectively referred to as a holographic lens unit 20.
  • the irradiation unit 4A has at least one light source 52 and at least one holographic lens unit 20, and from the viewpoint of increasing illuminance, it is preferable to have a plurality of holographic lens units 20 and light sources 52, and three It is more preferable to have the above.
  • the holographic lens units 20 are provided in correspondence with the light sources 52 in a one-to-one connection.
  • a holographic lens 21 which will be described later, is provided inside the contact lens 10 in the radial direction with respect to the light source 52 so that light from the light source can be irradiated into the eye.
  • the number of holographic lens units 20 and the number of light sources 52 are the same.
  • the irradiation unit 4A further includes a light source drive circuit 51 that drives the light source 52, for example.
  • the light source drive circuit 51 includes, for example, a light source 52 and a circuit that drives the light source 52.
  • the light source 52 is, for example, a substrate-stacked LED, a halogen lamp, a xenon lamp, or the like.
  • the light source drive circuit 51 is provided within the second region 2 of the contact lens 10, for example.
  • power is supplied to the light source drive circuit 51 and the light source 52 from outside the contact lens type intraocular illumination device 100A.
  • the connection between the light source drive circuit 51 and the power source 50 may be a wireless connection or a wired connection.
  • the power source 50 is, for example, a wireless drive power source provided outside the contact lens 10, and wirelessly supplies power to the light source drive circuit 51.
  • a power supply circuit 53 is provided in the second region 2 and the third region 3 of the contact lens 10 .
  • the plurality of holographic lens units 20 are arranged side by side on the same circumference equidistant from the center of the contact lens 10 in plan view. By arranging the holographic lens units 20 along the circumference, variations in intraocular illuminance can be suppressed in the radial direction of the contact lens 10. It is preferable that the plurality of holographic lens units 20 are arranged rotationally symmetrically with respect to the circle center of the contact lens 10 when the contact lens 10 is viewed from above. Since the plurality of holographic lens units 20 are arranged rotationally symmetrically with respect to the circle center of the contact lens 10, variations in illuminance in the circumferential direction of the contact lens 10 can be suppressed.
  • FIG. 2 shows an example in which four holographic lens units 20 are arranged 90° rotationally symmetrically on the same circumference equidistant from the center of the contact lens 10 in plan view.
  • the number of units 20 can be arbitrary, and their arrangement can also be arbitrary.
  • the contact lens type intraocular illumination device 100A has, for example, three holographic lens units 20, which may be arranged 120° rotationally symmetrically with respect to the circle center of the contact lens 10, and six holographic lens units. 20, and may be arranged 60° rotationally symmetrically with respect to the center of a circle when the contact lens 10 is viewed from above.
  • Each of the holographic lens units 20 is electrically connected to, for example, the holographic lens 21 that refracts the light supplied from the light source 52 and guides it into the eye, and the holographic lens 21, and controls the direction of the holographic lens 21. It has a holographic lens drive circuit 22 that changes.
  • the holographic lens 21 is supported by the contact lens 10 with a degree of freedom of movement. For example, the holographic lens 21 is supported so that the angle of the incident surface of the holographic lens 21 into which the light from the light source 52 is incident can be changed with respect to the incident light.
  • the holographic lens 21 and the light source 52 are arranged on the inner peripheral surface side of the contact lens 10 (the side closer to the eye).
  • the holographic lens 21 is provided between the center position in the thickness direction of the second region 2 and the inner circumferential surface 2A, and is preferably provided on the inner circumferential surface 2A of the second region 2.
  • the holographic lens 21 is moved relative to the contact lens 10 by a signal from the holographic lens drive circuit 22, and the traveling direction of the light and its spread angle are changed as the holographic lens 21 moves.
  • the contact lens type intraocular illumination device is manufactured by a method including, for example, a step of manufacturing a contact lens (lens manufacturing step) and a step of forming an irradiation unit on the contact lens (irradiation unit formation step). Ru.
  • members constituting the contact lens 10 are manufactured. For example, two members having the same shape in plan view are formed, which become the contact lens 10 by overlapping in the thickness direction.
  • the members constituting the contact lens 10 are manufactured by, for example, lace cutting, spin casting, molding, or the like.
  • the irradiation unit 4A is formed in the area that will become the second area 2 of the contact lens 10.
  • the irradiation unit 4A is mounted on one surface of the member constituting the contact lens 10.
  • the surface on which the irradiation unit 4A is mounted is the inner surface of the contact lens 10. In other words, it is the side facing away from the operator.
  • the members constituting the contact lens 10 are stacked so that the irradiation unit 4A is sandwiched between the members constituting the contact lens 10.
  • an antireflection film 30 is formed on the surface of the contact lens 10 that is opposite to the mounting surface 3A.
  • the antireflection film 30 is formed using, for example, a transparent adhesive.
  • the contact lens type intraocular illumination device 100A is easily attached to a patient's eye, for example, in a manner similar to the method of attaching a general vision correction contact lens.
  • the third region 3 is placed in contact with the sclera 73, thereby placing the first region 1 and the second region 2 above the cornea.
  • an instruction input is given to the light source drive circuit 51 from the outside, power is supplied from the power source 50 to the light source 52, and light is emitted from the light source 52, the light is emitted into the eye via the holographic lens 21.
  • the holographic lens drive circuit 22 drives the holographic lens 21 and adjusts the irradiation position as appropriate depending on the orientation of the holographic lens 21. be able to. As a result, light is irradiated to any position within the eye, such as the crystalline lens, vitreous body, and fundus.
  • the irradiation unit 4A is provided in the second region 2 of the scleral lens, adjusts the refraction of the light supplied from the light source 52, and directs the light into the eye. Because it irradiates light, the surgeon can irradiate light into the eye during surgery without having to use an intraocular illumination device. Therefore, the contact lens type intraocular illumination device 100A according to this embodiment is suitable for intraocular treatment using dual techniques. Furthermore, since there is no need to provide a port in the sclera 73 or the like for inserting an intraocular illumination device, the risk of infection can be reduced. Furthermore, since various parts of the eye can be irradiated simply by attaching the contact lens type intraocular illumination device 100A to the eye, it is possible to provide a highly versatile illumination device that can be applied to various surgeries.
  • the contact lens type intraocular illumination device 100A is suitable for long-term use such as intraocular surgery.
  • the contact lens 10 of the contact lens type intraocular illumination device 100A is provided so that the third region 3 is in contact with the sclera 73, and the irradiation unit 4A is formed in the second region 2.
  • the position of the interior lighting device 100 is difficult to shake. Specifically, the contact lens 10 is strongly supported between the sclera 73 and the eyelid in the third region 3, and the movement of the contact lens 10 itself is reduced. Further, even if eye movements occur during surgery, the positional deviation can be reduced. Therefore, according to the contact lens type intraocular illumination device 100, it is possible to reduce variations in illuminance over time to a specific position within the eye, and visibility during surgery is stabilized, thereby further stabilizing the observation system. You can also.
  • the present invention is not limited to the contact lens type intraocular illumination device 100A according to the above embodiment, and can be modified as appropriate within the scope of the gist of the claims.
  • it may be a contact lens type intraocular illumination device in which the antireflection film 30 is not provided.
  • the irradiation unit 4A may be mounted in contact with the second region 2 of the contact lens 10.
  • FIGS. 1 to 3 show an example in which the light source 52 is formed in the second region 2 of the contact lens 10, the light source may be located outside the contact lens 10.
  • the light source is arranged side by side with the contact lens 10 in the outer circumferential direction of the contact lens 10 .
  • the light source emits highly directional light.
  • the light from the light source passes through the third region 3 and is irradiated into the contact lens 10, is reflected inside the contact lens 10, enters the holographic lens 21, and is refracted by the holographic lens 21 to enter the eye. irradiate.
  • FIGS. 1 to 3 show an example in which the power source 50 is provided outside the contact lens 10 and connected to the light source 52 by wire or wirelessly, the power source 50 may be provided outside the contact lens 10. good.
  • the power source 50 may be provided within the second region 2.
  • the power sources 50 may be provided in correspondence with the number of light sources 52, or may be provided in a number smaller than the number of light sources 52.
  • a conductive wire connected to the power sources 50 is provided in the second region 2 of the contact lens 10 along the shape of the second region 2, and is connected to the plurality of light sources 52. You can leave it there. In such a configuration, the plurality of light sources 52 are connected in parallel.
  • FIG. 4 is a sectional view showing a modification of the contact lens type intraocular illumination device of FIG. 1.
  • structures similar to those in FIGS. 1 to 3 are denoted by the same reference numerals, and explanations thereof will be omitted.
  • illustration of the patient's eye is omitted, and only the symbol (S2) indicating that it is intraocular is shown.
  • the contact lens type intraocular illumination device 100X shown in FIG. a contact lens 10X including a ring-shaped second region 2, and an irradiation unit provided in the second region 2 of the contact lens 10X, which adjusts the refraction of the light supplied from the light source 52 and irradiates the light into the eye. Equipped with 4A.
  • the contact lens 10X differs from the contact lens 10 in that it does not include the first region 1.
  • the contact lens 10X includes, for example, a second region 2 and a third region 3, and further includes an antireflection film 30 on the surface opposite to the mounting surface 3A.
  • the contact lens type intraocular illumination device 100X is manufactured, for example, by a method that further includes an opening step of forming an aperture at the center of the contact lens 10 in plan view after manufacturing the contact lens type intraocular illumination device 100.
  • the present invention may be, for example, a contact lens type intraocular illumination device 100B as shown in FIG.
  • FIG. 5 is a sectional view showing an example of the configuration of a contact lens type intraocular illumination device according to another embodiment of the present invention, and FIG. FIG. In FIG. 5, for convenience of explanation, light irradiated into the eye is indicated by a chain double-dashed line.
  • a contact lens type intraocular illumination device 100B shown in FIGS. 5 and 6 is provided in a contact lens 10 and a second region 2 of the contact lens 10, and adjusts the diffusion of light supplied from a light source to bring light into the eye.
  • At least one irradiation unit 4B is provided, preferably a plurality of irradiation units 4B, and more preferably three or more.
  • the irradiation unit 4B diffusely reflects the light supplied from the light source and irradiates the inside of the eye with the light.
  • the irradiation unit 4B is provided within the second region 2 of the contact lens 10, for example.
  • the irradiation unit 4B plays the role of illuminating the inside of the patient's eye.
  • the irradiation unit 4B irradiates the inside of the patient's eye so that the central illuminance at the fundus is 10,000 to 100,000 lx.
  • the above illuminance is based on JIS Z9110:2010.
  • the irradiation unit 4B includes a light guide plate 41A that guides the light supplied from the light source 52 to the diffusion sheet 42A, and at least one diffusion sheet 42A that is laminated on the light guide plate 41A and diffuses the light from the light guide plate 41A and guides it into the eye. have one each.
  • the light guide plate 41A and the diffusion sheet 42A will be collectively referred to as an optical stack unit 40A.
  • the irradiation unit 4B has at least one light source 52 and at least one optical laminated unit 40A, and from the viewpoint of increasing illuminance, it is preferable to have a plurality of light sources 52 and optical laminated units 40A.
  • the optical stack unit 40A is provided in a one-to-one connection corresponding to the light source 52.
  • an optical laminated unit 40A which will be described later, is provided on the inner circumferential surface side (closer to the eye) of the contact lens 10 with respect to the light source 52.
  • the number of optical stack units 40A and light sources 52 is the same.
  • the irradiation unit 4B further includes a light source drive circuit 51 that drives the light source 52, for example.
  • the light source drive circuit 51 includes, for example, a light source 52 and a circuit that drives the light source 52.
  • the light source 52 included in the light source drive circuit 51 is arranged so as to irradiate light onto the light guide plate 41A.
  • the plurality of optical laminated units 40A are preferably arranged on the same circumference equidistant from the center of a circle when the contact lens 10 is viewed from above. By arranging the optical laminated units 40A on the circumference, variations in intraocular illuminance in the radial direction of the contact lens 10 can be suppressed. It is preferable that the plurality of optical laminated units 40A are arranged rotationally symmetrically with respect to the circle center of the contact lens 10 in a plan view of the contact lens 10. By arranging the plurality of optical laminated units 40A rotationally symmetrically with respect to the circle center of the contact lens 10, variations in illuminance in the circumferential direction of the contact lens can be suppressed.
  • FIG. 6 shows an example in which four optical laminated units 40A are arranged 90° rotationally symmetrically on the same circumference equidistant from the center of the contact lens 10 in a plan view.
  • the number can be arbitrary, and the arrangement thereof can also be arbitrary.
  • the contact lens type intraocular illumination device 100B has, for example, three optical laminated units, which may be arranged 120° rotationally symmetrically with respect to the center of a circle when the contact lens 10 is viewed in plan, and six optical laminated units. It may have an optical laminated unit and be arranged 60° rotationally symmetrically with respect to the center of a circle when the contact lens 10 is viewed from above.
  • Each of the optical lamination units 40A includes, for example, a light guide plate 41A and a diffusion sheet 42A that is laminated on the inner peripheral surface side of the contact lens 10 with respect to the light guide plate 41A.
  • the light guide plate 41A and the diffusion sheet 42B are arranged substantially perpendicular to the thickness direction of the contact lens 10.
  • the thickness of the diffusion sheet 42A is, for example, greater than the thickness of the light guide plate 41A.
  • the light guide plate 41A emits light that has entered from the side surface of the light guide plate 41A from its main surface, and guides the light to the diffusion sheet 42B.
  • the diffusion sheet 42B transmits and diffuses light incident from one main surface, and emits the diffused light from the other main surface.
  • the optical laminated unit 40A and the light source 52 are arranged on the inner peripheral surface side of the contact lens 10.
  • the end face on the inner peripheral surface side of the optical laminated unit 40 is provided between the center position in the thickness direction of the second region 2 and the inner peripheral surface 2A, and preferably is provided on the inner peripheral surface 2A of the second region 2. It is being By arranging the light guide plate 41A and the diffusion sheet 42A in this manner, illuminance and intensity can be ensured.
  • the contact lens type intraocular illumination device 100B like the contact lens type intraocular illumination device 100A, is easily attached to the patient's eye, and the third region 3 is placed in contact with the sclera 73. Then, when an instruction input is given to the light source drive circuit 51 from the outside, power is supplied from the power source 50 to the light source 52, and light is irradiated from the light source 52, the light enters the diffusion sheet 42A via the light guide plate 41A. The diffused light generated by this is irradiated into the eye. As a result, light is irradiated to any position within the eye, such as the crystalline lens, vitreous body, and fundus.
  • the irradiation unit 4B is provided in the second region 2 of the scleral lens, adjusts the diffusion of the light supplied from the light source 52, and injects the light into the eye. Since light is irradiated, the operator can irradiate light into the eye during surgery without holding an intraocular illumination device. Therefore, the contact lens type intraocular illumination device 100B according to this embodiment is suitable for intraocular treatment using dual techniques. Further, since there is no need to provide a port in the sclera 73 or the like for inserting the intraocular illumination device, the risk of infection can be reduced. Furthermore, since various parts of the eye can be irradiated simply by attaching the contact lens type intraocular illumination device 100B to the eye, it is possible to provide a highly versatile illumination device that can be applied to various surgeries.
  • the contact lens type intraocular illumination device 100B is suitable for long-term use such as intraocular surgery.
  • FIG. 7 is a plan view showing a modification of the contact lens type intraocular illumination device of FIG. 6.
  • a contact lens type intraocular illumination device 100C shown in FIG. 7 is an irradiation unit that is provided in the contact lens 10 and the second region 2, and adjusts the reflection of light supplied from a light source 52 to irradiate light into the eye. Equipped with 4C.
  • the irradiation unit 4C includes, for example, a light guide plate 41B having an annular shape in plan view, and a diffusion sheet 42B having an annular shape in plan view, which is laminated on the inner peripheral surface side (the side closer to the eyes) of the light guide plate 41B. Equipped with.
  • the light guide plate 41B and the diffusion sheet 42B are collectively referred to as an optical stack unit 40B.
  • the thickness of the diffusion sheet 42B is greater than, for example, the thickness of the light guide plate 41A.
  • the contact lens type intraocular lighting devices 100B and 100C are manufactured by the same method as the contact lens type intraocular lighting device 100A, except that the irradiation unit 4B or 4C is formed in the irradiation unit forming step.
  • the number of light sources 52, the number of light guide plates 41A and 41B, and the number of diffusion sheets 42A and 42B are the same, but they do not need to be the same number.
  • more light sources 52 than light guide plates 41A, 41B may be formed, and one light guide plate 41A, 41B may be irradiated with light from a plurality of light sources. With this configuration, the illuminance can be further increased.
  • the number of light guide plates 41A, 41B may be greater than the number of diffusion sheets 42A, 42B, and one diffusion sheet 42A, 42B and a plurality of light guide plates 41A, 41B may be stacked.
  • FIG. 8 is a sectional view showing a modification of the contact lens type intraocular illumination device of FIG. 5.
  • structures similar to those in FIGS. 1 to 3 are denoted by the same reference numerals, and explanations thereof will be omitted.
  • the contact lens type intraocular illumination device 100Y shown in FIG. 8 includes a ring-shaped third region 3 provided in contact with the sclera 73, and a ring-shaped third region 3 extending radially inward from the inner circumference of the third region 3.
  • the contact lens 10X differs from the contact lens 10 in that it does not include the first region 1.
  • the contact lens 10X includes, for example, a second region 2 and a third region 3, and further includes an antireflection film 30 on the surface opposite to the mounting surface 3A.
  • the contact lens type intraocular illumination device 100Y is manufactured, for example, by a method that further includes an opening step of forming an aperture at the center of the contact lens 10 in plan view after manufacturing the contact lens type intraocular illumination device 100.
  • the conventional technology required the intraocular illumination device to be supported with one hand, but the use of the contact lens-type intraocular illumination device of the above embodiment enables a dual technique and is effective. It is.
  • intrascleral entrapment surgery for retinal detachment conventional technology required a complicated procedure using a binocular indirect mirror to observe the fundus, whereas the contact lens-type intraocular illumination device of the above embodiment By using a wide-angle fundus observation system, fundus observation becomes easy and effective.

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  • Health & Medical Sciences (AREA)
  • Ophthalmology & Optometry (AREA)
  • Physics & Mathematics (AREA)
  • General Health & Medical Sciences (AREA)
  • General Physics & Mathematics (AREA)
  • Optics & Photonics (AREA)
  • Prostheses (AREA)
PCT/JP2023/029230 2022-08-10 2023-08-10 コンタクトレンズ型眼内照明機器 Ceased WO2024034658A1 (ja)

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Citations (7)

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JP2016165479A (ja) * 2011-02-04 2016-09-15 ジョンソン・アンド・ジョンソン・ビジョン・ケア・インコーポレイテッドＪｏｈｎｓｏｎ ＆ Ｊｏｈｎｓｏｎ Ｖｉｓｉｏｎ Ｃａｒｅ， Ｉｎｃ． 眼鏡フレーム及びコンタクトレンズを備える光線療法システム
JP2019511273A (ja) 2016-03-31 2019-04-25 ノバルティス アーゲー 眼科手術のための可視化システム
JP2021508860A (ja) 2017-12-21 2021-03-11 ファイ・バイオメッド・インコーポレイテッド 無線駆動スマートコンタクトレンズ
WO2021148548A1 (fr) * 2020-01-21 2021-07-29 Institut Mines Telecom Lentille de contact pour réalité augmentée et procédé correspondant
JP2021522925A (ja) * 2018-05-10 2021-09-02 アキュセラ インコーポレイテッド 眼の屈折異常を処置するための方法および装置
JP2022508709A (ja) 2018-10-13 2022-01-19 プレベンタ メディカル コーポレイション 照射式コンタクトレンズ並びに改善された眼診断、疾病管理及び手術のためのシステム
JP2022128395A (ja) 2021-02-22 2022-09-01 財團法人工業技術研究院 閉端型燃料電池およびそのアノード双極板

Patent Citations (7)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
JP2016165479A (ja) * 2011-02-04 2016-09-15 ジョンソン・アンド・ジョンソン・ビジョン・ケア・インコーポレイテッドＪｏｈｎｓｏｎ ＆ Ｊｏｈｎｓｏｎ Ｖｉｓｉｏｎ Ｃａｒｅ， Ｉｎｃ． 眼鏡フレーム及びコンタクトレンズを備える光線療法システム
JP2019511273A (ja) 2016-03-31 2019-04-25 ノバルティス アーゲー 眼科手術のための可視化システム
JP2021508860A (ja) 2017-12-21 2021-03-11 ファイ・バイオメッド・インコーポレイテッド 無線駆動スマートコンタクトレンズ
JP2021522925A (ja) * 2018-05-10 2021-09-02 アキュセラ インコーポレイテッド 眼の屈折異常を処置するための方法および装置
JP2022508709A (ja) 2018-10-13 2022-01-19 プレベンタ メディカル コーポレイション 照射式コンタクトレンズ並びに改善された眼診断、疾病管理及び手術のためのシステム
WO2021148548A1 (fr) * 2020-01-21 2021-07-29 Institut Mines Telecom Lentille de contact pour réalité augmentée et procédé correspondant
JP2022128395A (ja) 2021-02-22 2022-09-01 財團法人工業技術研究院 閉端型燃料電池およびそのアノード双極板

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