WO2010064278A1 - Procédé de conception de lentille ophtalmique, lentille ophtalmique et dispositif d'opération de correction de réfraction - Google Patents

Procédé de conception de lentille ophtalmique, lentille ophtalmique et dispositif d'opération de correction de réfraction Download PDF

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Publication number
WO2010064278A1
WO2010064278A1 PCT/JP2008/003582 JP2008003582W WO2010064278A1 WO 2010064278 A1 WO2010064278 A1 WO 2010064278A1 JP 2008003582 W JP2008003582 W JP 2008003582W WO 2010064278 A1 WO2010064278 A1 WO 2010064278A1
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axis
optical
deviation
ophthalmic lens
anatomical
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PCT/JP2008/003582
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English (en)
Japanese (ja)
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柏木豊彦
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Kashiwagi Toyohiko
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Priority to PCT/JP2008/003582 priority Critical patent/WO2010064278A1/fr
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    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
    • A61F2/02—Prostheses implantable into the body
    • A61F2/14—Eye parts, e.g. lenses, corneal implants; Implanting instruments specially adapted therefor; Artificial eyes
    • A61F2/16—Intraocular lenses
    • A61F2/1613—Intraocular lenses having special lens configurations, e.g. multipart lenses; having particular optical properties, e.g. pseudo-accommodative lenses, lenses having aberration corrections, diffractive lenses, lenses for variably absorbing electromagnetic radiation, lenses having variable focus
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B3/00—Apparatus for testing the eyes; Instruments for examining the eyes
    • A61B3/0016—Operational features thereof
    • A61B3/0025—Operational features thereof characterised by electronic signal processing, e.g. eye models
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
    • A61F2240/00—Manufacturing or designing of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
    • A61F2240/001—Designing or manufacturing processes
    • A61F2240/002—Designing or making customized prostheses

Definitions

  • the present invention relates to a novel design method relating to an eye refractive correction means, and an ophthalmic lens and a refractive surgery apparatus obtained by using the same, and in particular, the retinal fovea of the eye has an anatomical eye axis or an optical axis of the eye. Focusing on the deviation from the above, a method for improving the performance of the conventional ophthalmic lens and the quality of the corneal refractive surgery device in the sense of ensuring a clear image at the fovea of the retina, and the eye The present invention also relates to a method for manufacturing an ophthalmic lens, and to an ophthalmic lens and a corneal refractive surgery device manufactured as described above.
  • optical axis 1 and optical axis 2 When an optical axis is defined for a refracting surface or an optical system, the shape or refractive index distribution of the refracting surface or the optical system has a rotationally symmetric axis with respect to the optical axis or at least two including the optical axis
  • the refractive surface, the shape of the optical system, and the refractive index distribution are plane-symmetric with respect to the above plane, their optical axes are taken as the optical axis 1.
  • the optical axis is not the optical axis 1, the optical axis is the optical axis 2.
  • the refracting surface that can define the optical axis 1 is, for example, a straight line passing through the center of the spherical surface in a spherical surface.
  • the rotational symmetry axis of an aspherical refracting surface that has a symmetrical shape with respect to the rotational symmetry axis.
  • the perpendicular line standing on the axis of the cylinder is the optical axis 1.
  • the toric surface is generally a curved surface formed by rotating a line-symmetric plane figure on the plane and having a straight line perpendicular to the line-symmetric axis as an axis.
  • the line-symmetric axis is the optical axis 1.
  • Refractive surfaces that cannot define the optical axis 1 are irregular refracting surfaces, conical surfaces, and the like.
  • the optical system has the optical axis 1 when all the refracting surfaces have the optical axis 1 and all the optical axes 1 overlap, and the optical system is called a coaxial optical system. If the optical axis 1 of some refractive surfaces does not overlap with the optical axis 1 of other refractive surfaces, the optical axis 1 cannot be defined in the optical system. It is also possible to define the optical axis 2 with respect to a refractive surface that can define the optical axis 1.
  • the optical axis refers to the optical axis 1 and the optical axis 2, and the optical axis 1 and the optical axis 2 will be described separately when necessary.
  • Deviation means both translation and tilting or rotation.
  • the deflection of the refracting surface means that the optical axis 1 or the optical axis 2 is displaced.
  • Anatomical corneal center anatomical corneal axis definition
  • the limbus is approximated by a circumference or an ellipse, and a straight line that passes through the circumference or the center of the ellipse (the midpoint between the two focal points) and is perpendicular to the plane containing the circumference or the ellipse is defined as the anatomical corneal axis.
  • the intersections of the anatomical corneal axis with the anterior corneal surface and the posterior corneal surface are the anatomical cornea centers of the anterior and corneal surfaces, respectively.
  • corneal optical center and corneal optical axis The definition of the corneal optical axis is sometimes defined as a straight line connecting the centers of curvature of the anterior and posterior surfaces of the cornea, but is theoretically often defined as an anatomical corneal axis. However, in actual measurement, a center or axis different from the anatomical corneal center or the anatomical corneal axis is used as the corneal center or the optical axis of the cornea.
  • many corneal shape measuring devices display the corneal shape with reference to a point (sighting line) deviated from the anatomical cornea center, and such a sighting line can be used as the corneal optical axis.
  • the corneal refracting surface may not be axisymmetric or plane symmetric with respect to the corneal optical axis, but the optical axis in this case is the optical axis 2.
  • the point where the corneal optical axis and the cornea intersect is the center of the corneal optical axis.
  • the anatomical corneal axis is defined as the contact lens support reference axis.
  • the outer edge of a contact lens is almost a circle. Approximate the outer edge of the contact lens with an approximate circumference or ellipse, and use the plane containing the circumference or ellipse as the contact lens supported reference plane, and contact the perpendicular line from the center of the circumference or ellipse to the supported reference plane.
  • the point where the supported central axis and the contact lens rear surface (surface in contact with the cornea) intersect is defined as the contact lens supported center.
  • the outer edge of the soft contact lens is supported in the vicinity of the corneal ring, and the entire contact lens is supported in contact with the front surface of the cornea. Since the movement is relatively small, the contact lens support reference axis and the contact lens supported central axis almost coincide. . Further, when the contact lens supported center is supported by the anatomical cornea center in a state of good conformity even with a hard contact lens, the contact lens supported center axis and the contact lens support reference axis coincide with each other.
  • the locations where the intraocular lens is supported in the eye include the anterior chamber corner, the iris, the lens capsule, the ciliary groove, and the sclera.
  • the tip of the intraocular lens supported portion is supported so as to contact the anterior chamber corner.
  • the supported portion is supported on the iris surface.
  • the supported portion is supported substantially on the circumference of the outermost periphery of the lens capsule, and at the same time, the rear surface or front surface of the optical unit is supported so as to contact the rear surface or front surface of the lens capsule.
  • the intraocular lens supported portion is supported so as to contact the ciliary groove or sclera.
  • Intraocular lens support reference plane intraocular lens support center and support reference axis
  • the inner lens support reference plane the plane determined by the approximate circumference
  • the center of the circumference is the intraocular lens support center.
  • a straight line that passes through the intraocular lens support center and is perpendicular to the support reference plane is defined as an intraocular lens support reference axis.
  • the front or rear of the iris is substantially on a plane, so that the plane is the intraocular lens support reference plane, and the supported part of the intraocular lens is supported by the iris in two, three, or
  • the center of the plurality of supported parts is defined as a support center
  • a straight line passing through the support center and perpendicular to the support reference plane is defined as a support reference axis.
  • the support reference plane and the support reference axis are defined in the same manner as the anterior chamber corner and the capsular bag in consideration of the approximate circumference determined by the portion to be sewn.
  • the supported part of the intraocular lens refers to a part excluding the optical part of the intraocular lens.
  • the shape of the intraocular lens supported part is generally one in which two loops or branch structures called haptics are attached to extend from the optical part.
  • haptics are attached to extend from the optical part.
  • a flat plate-like structure extends from the optical portion to the peripheral portion, and the plate-like tip portion contacts the intraocular structure.
  • the plate-like tip may have two, four or circumferential shapes, or three.
  • the intraocular lens may be supported only by the supported part, or may be supported by both the supported part and the optical part.
  • the inner diameter of the right circular cylinder is substantially equal to the diameter of the circumference of the portion where the intraocular lens is actually supported in the eye Support with.
  • connects the inner surface of a right cylinder makes it the same height from the bottom face of a right cylinder. Then, the plurality of curved portions are supported on the circumference or substantially the circumference of the inner surface of the right circular cylinder.
  • the plane including the circumference is the intraocular lens supported reference plane, and the axis of the right circular cylinder is the intraocular lens supported central axis.
  • the intersection of the intraocular lens supported reference plane and the intraocular lens supported central axis is the intraocular lens supported center.
  • the intraocular lens supported portion When there are two intraocular lens supported portions, as shown in FIG. 2a, the intraocular lens supported portion is inserted into the right circular cylinder, and the two supported portions are in contact with the inner side of the right circular cylinder.
  • the height from the bottom of the right circular cylinder is the same.
  • the plane is supported so as to be parallel to the bottom surface of the cylinder.
  • the rotational symmetry axis of the right circular cylinder becomes the supported central axis, and the plane parallel to the bottom surface of the cylinder at the height where the cylindrical inner surface and the supported portion are in contact is the supported reference plane. .
  • the intersection of the supported central axis and the supported reference plane is the supported center.
  • the two planes are extended so that the straight line where the two planes intersect is parallel to the bottom surface of the right circular cylinder.
  • the rotationally symmetric axis of the right circular cylinder becomes the supported central axis, and the plane parallel to the bottom surface of the cylinder at the height where the cylindrical inner surface and the supported portion are in contact is the supported reference plane.
  • the intersection of the supported center axis and the supported reference plane is the supported center.
  • the equator of the lens is substantially on the circumference, and the center of the circumference is the center of the lens.
  • a straight line connecting the center of the corneal limbus and the center of the lens is defined as the anatomical eyeball axis.
  • the anatomical eyeball axis is the optical axis of the eyeball.
  • the plane including the circumference of the crystalline lens equator that is, the intraocular lens support reference plane is perpendicular to the anatomical eyeball axis, in which case the intraocular lens support reference axis coincides with the anatomical eyeball axis.
  • the intraocular lens support reference axis does not match the anatomical eye axis.
  • the inner lens support reference axis overlaps the anatomical eye axis. However, when there is an anatomical deviation, the anatomical eyeball axis does not coincide with the intraocular lens support reference axis.
  • Anatomical eye axis Intraocular lens support reference axis (normal eyeball)
  • Anatomic eyeball axis not Intraocular lens support reference axis (for anatomically misaligned eyeballs) It becomes.
  • the soft and hard lenses also have the same anatomical corneal center and hard contact lens supported center, and the anatomical eyeball axis and anatomical corneal axis coincide (usually coincident).
  • Anatomical corneal axis contact lens support reference axis (always established by definition)
  • the retinal fovea is displaced to the ear side by about 1.4 mm from the anatomical eye axis. See FIGS.
  • the corneal optical axis is selected to coincide with the anatomical eyeball axis, and in this case as well, the retinal fovea is offset from the corneal optical axis.
  • the corneal optical axis is selected so that the retinal fovea is on the corneal optical axis, there is no guarantee that the corneal refractive surface is optically symmetric or plane-symmetric with respect to the corneal optical axis.
  • the corneal optical axis coincides with the intraocular lens support reference axis.
  • a corneal optical axis deviated from the anatomical eyeball axis is selected, and the corneal optical axis is the optical axis 1, and the retinal fovea is on the optical axis 1, and the optical axis 1 and the intraocular lens support reference If the axes match, there will be a coaxial optical system in the sense that all refractive surfaces of the optical system have a common optical axis 1 that is deviated from the anatomical eyeball axis. It is even rarer.
  • Spherical aberration is defined as an axially symmetric aberration with respect to the optical axis.
  • Spherical aberration is determined by the distance from the optical axis of a light beam incident on the optical system from an object point, and is represented by the amount of deviation from the paraxial image point.
  • the magnitude of the deviation is represented by the longitudinal aberration of the difference between the intersections intersecting the optical axis or the lateral aberration represented by the deviation from the paraxial image point on a plane standing perpendicular to the optical axis.
  • spherical aberration it is considered to be an aberration due to the refracting surface being made of a spherical surface, but it can be understood from the definition of spherical aberration, whether the optical system is spherical or aspherical.
  • Spherical aberration can be defined. Originally it should be called aperture aberration, but by convention it is called spherical aberration. An aberration having two symmetry planes is called astigmatism. An aberration having only one symmetry plane is called coma.
  • the specific direction is a direction in which the refractive surface of the eyeball optical system should be deviated from the anatomical eyeball axis in order to reduce the aberration at the fovea of the retina. it can.
  • an eyeball optical system in which an optical unit inserts an intraocular lens having an optical axis 1, when the corneal optical axis arbitrarily deviated from the anatomical eyeball axis is selected, the corneal optical axis becomes the optical axis 1, and the retina If the fovea is on its corneal optical axis 1 or if it is in the same direction as the deviation of the retinal fovea from the corneal optical axis 1 and the deviation of the corneal optical axis 1 from the anatomical eye axis When at least one refracting surface of the lens optical unit is deflected, the specific direction is the direction of deviation of the corneal optical axis from the anatomical eyeball axis.
  • the line of sight is deviated substantially horizontally from the anatomical eyeball axis.
  • the specific direction is substantially horizontal.
  • the optical axis 1 of the intraocular lens optical unit may be aligned with the line of sight. At this time, the optical axis of the intraocular lens optical unit is deviated from the anatomical eyeball axis.
  • the corneal shape analysis is performed with reference to the corneal optical axis deviated from the anatomical eyeball axis, and the corneal shape has one symmetry plane.
  • the symmetry plane and the direction of the corneal optical axis shift from the anatomical eye axis are parallel, and the retinal fovea is on the corneal optical axis or the retinal fovea is offset from the corneal optical axis.
  • the specific direction is the direction of deviation of the corneal optical axis from the anatomical eyeball axis.
  • the corneal optical axis is taken as the line of sight
  • the line of sight is deviated from the anatomical eyeball axis in a substantially horizontal direction, so that the specific direction is a substantially horizontal direction.
  • the corneal shape has a coma having an axis in the horizontal direction in the central retinal fossa.
  • the corneal shape is measured with reference to the corneal optical axis deviated from the anatomical eyeball axis, and the corneal shape has a plane of symmetry 2.
  • the corneal optical axis deviation from the anatomical eye axis is parallel to either of the symmetry planes, and the retinal fovea is on the corneal optical axis, or the deviation of the retinal fovea from the corneal optical axis If the direction is parallel to any of the planes of symmetry, the specific direction is the direction of deviation of the corneal optical axis from the anatomical eye axis.
  • the retinal fovea happens to be on the corneal optical axis. Either is a specific direction. This corresponds to the case where astigmatism, that is, astigmatism, exists in the retinal fovea with respect to the line of sight.
  • the visual axis is defined by a straight line connecting the retinal fovea and the object point corresponding to the retinal fovea.
  • a reference axis is used as a design reference axis when the position and inclination of the optical unit are represented by figures and numerical values. There are the following four methods for selecting the design reference axis and the central retinal fossa. a) Using the anatomical eye axis as the design reference axis, and assuming that the retinal fovea is on the design reference axis extension. b) When the anatomical eye axis is used as the design reference axis and the retinal fovea is not on the design reference axis extension.
  • the performance is evaluated by focusing on the performance on the anatomical eye axis. It will be. Therefore, it is not an intraocular lens design that improves the performance in the central retinal fovea.
  • Non-Patent Document 1 for the first time in 2007, focusing on the fact that the fovea of the retina is displaced from the anatomical eyeball to the ear side, Optimizing the ratio of the curvature of the front surface of the optical unit and the refractive power of the rear surface for each lens power in order to reduce the coma at the retinal fovea while keeping the optical axis of the intraocular lens coaxial.
  • An aspherical intraocular lens has been proposed.
  • the ratio of the refractive power of the front and rear surfaces of the optical part of the intraocular lens and the aspheric coefficient are determined for each lens power, and the degree of freedom in design is small.
  • the first claim of Patent Document 2 has an object of deviating the supported portion and the optical portion of the intraocular lens so that the center of the pupil coincides with the optical axis of the intraocular lens.
  • matching the pupil center with the optical axis of the intraocular lens is neither a necessary condition nor a sufficient condition in order to reduce the aberration at the retinal fovea. Rather, when the pupil center and the optical axis of the intraocular lens coincide with each other, the aberration at the retinal fovea may increase.
  • the second claim of Patent Document 2 aims to make the visual axis and the optical axis 1 of the intraocular lens coincide with each other.
  • the fact that the visual axis and the intraocular lens optical axis 1 coincide with each other is neither a necessary condition nor a sufficient condition for reducing the aberration at the retinal fovea.
  • the main factors that affect the aberrations in the fovea of the retina are the refractive power of the anteroposterior surface of the cornea, the aspherical shape of the anteroposterior surface of the cornea, the depth of the pupil, the positional deviation of the pupil from the anatomical eye axis, and the pupil Size, refractive power of the whole optical part of the intraocular lens, refractive power ratio of the front and rear surfaces of the optical part, aspherical aspect of the ophthalmic lens refractive surface, deviation of the ophthalmic lens refractive surface, position of the central retina, Such as the axial length.
  • Patent Document 3 discloses an idea of calculating the intraocular lens power using ray tracing in consideration of the fact that the fovea of the retina is displaced from the optical axis of the cornea.
  • the idea of making the intraocular lens non-coaxial with the optical axis of the cornea is not seen in the patent document, and only refers to the optical part of the intraocular lens, and the intraocular lens optical part and the intraocular lens supported part. There is no mention of any relationship.
  • Non-Patent Document 2 suggests that the corneal coma may be corrected by the displacement of the intraocular lens.
  • coma aberration is mentioned, and there is no mention of other spherical aberration and astigmatism that affect the image at the fovea of the retina.
  • astigmatism and the like also appear in the retinal fovea due to the deviation of the intraocular lens as shown in the drawings described later.
  • Non-Patent Document 1 overcomes the complexity of determining the aspherical coefficient by changing the refractive power ratio between the front and back surfaces of the intraocular lens for each lens power, and using a relatively simple method. To provide a method of reducing aberrations in the fovea. Increase design freedom.
  • the means according to the present invention for solving the above-mentioned problems includes at least one refracting surface in order to deviate the optical axis of at least one refracting surface of the ophthalmic lens optical unit from the anatomical eyeball axis.
  • the main feature is that it is deviated from the central axis of the ophthalmic lens supported. See FIG. The same method is applied to corneal refractive surgery.
  • the method for determining the deviation of the refractive surface of the eyeball optical system comprises a step 1 of creating a mathematical model of an eyeball optical system having a retinal fovea displaced from the anatomical eyeball axis in a computer, and the eyeball Performing at least one back ray tracing from the fovea of the retina to the eyeball optical system using the step 2 of deflecting at least one refractive surface of the optical system and the mathematical model in the computer Step 3 for obtaining an object point corresponding to the retinal fovea, Step 4 for tracing a plurality of rays emitted from the object point, obtaining an image evaluation means in the vicinity of the retinal fovea, and Steps 2 to 4 Step 5 for obtaining a plurality of the image evaluation means corresponding to a plurality of deviations of at least one refracting surface of the eyeball optical system is repeatedly used with the plurality of image evaluation means.
  • FIG. 2b shows the retinal fovea, the object points corresponding to the retinal fovea, the anatomical eye axis (anatomical eye axis), and the visual axis.
  • FIG. 3 shows a flow chart of the design method.
  • the angle of a plurality of light rays emitted from an object point is determined by taking a straight line passing through the object point and being parallel to the optical axis as a Z axis, and taking an orthogonal coordinate system X, Y axis perpendicular to the Z axis,
  • the angles between the plane and the ZX plane are ⁇ x and ⁇ y
  • the minute angles are d ⁇ , m, and n as integers.
  • the cornea optical model corresponding to the corneal optical system is not limited to a spherical surface but may be an aspherical surface, a toric surface, an ellipsoidal surface, or a refractive surface having no rotational symmetry axis.
  • An aspherical surface can also be defined by approximating with a polynomial, a refractive index distribution type, or by designating the surface inclination at each point on the surface of the refractive surface.
  • the average shape of the cornea obtained from actual measurement can be used.
  • the front and rear corneal curvature radii can be variously changed by using an average corneal curvature radius obtained by actual measurement.
  • the corneal thickness can also be changed using the thickness obtained from actual measurement.
  • the refractive index of the Gullstran model eye can also be adopted.
  • the measurement center often does not coincide with the anatomical eye axis or the anatomical cornea center, so the corneal optical axis does not need to coincide with the anatomical eye axis.
  • the corneal shape can be modeled in the computer based on the corneal optical axis from the measured value. This operation is not difficult for those skilled in the art.
  • the shape of the pupil can be circular, elliptical, or other shapes.
  • the size of the pupil can be changed according to the actual state.
  • the position of the pupil in the optical axis direction that is, the pupil depth can be changed based on the actual measurement result.
  • the position in the plane perpendicular to the optical axis direction of the pupil can make the center of the pupil coincide with the anatomical eyeball axis, or the pupil center can be displaced from the anatomical eyeball axis.
  • the pupil center is shifted from the center of the cornea to the nasal side by about 0.3 mm on average when the eyeball is viewed from the front, but in extreme cases it may be shifted by 0.6 mm, so use that value. You can also
  • the inclinations ⁇ x and ⁇ y of the starting ray passing through the pupil boundary point are obtained as follows.
  • the position and size of the entrance pupil are obtained by paraxial reverse ray tracing.
  • the initial value of the inclination of the starting ray is determined so that the boundary point of the entrance pupil corresponding to the boundary point of the pupil is seen from the starting point, and the ray is traced with respect to the inclination to intersect the pupil plane, and Find the distance to the boundary point.
  • the inclination of the starting ray passing through the boundary point of the pupil can be obtained by changing the inclination of the starting ray using a sequential calculation such as Newton's method until the distance becomes substantially zero.
  • a spherical surface, a cylindrical surface, a toric surface, an aspherical surface, a diffractive element surface, or the like can be used.
  • Aspherical surfaces are not limited to aspherical surfaces determined by aspherical coefficients using polynomials used in lens design etc., but aspherical surfaces of all shapes that are rotationally symmetric and aspherical surfaces that do not have rotationally symmetric axes or plane symmetry axes should be used. it can.
  • the ophthalmic lens optical unit may be a gradient index lens.
  • Ray tracing with respect to the diffractive element surface can be performed by dividing the light beam reaching the diffractive element surface into a plurality of light beams corresponding to the diffracting direction and tracing the light beam.
  • the ratio of the front and rear refractive powers can be arbitrarily selected.
  • mathematical models such as a front convex meniscus lens, a convex flat lens, a biconvex lens, a plano-convex lens, and a rear convex meniscus lens can be created in the computer.
  • the incident light, the outgoing light, the normal of the refracting surface, etc. are all expressed by vectors, and when calculating the intersection, it is possible to simplify the calculation formula and program by using the vector equation. Further, when obtaining the intersection point, the intersection point may be obtained by sequential calculation. However, using the Newton method is versatile and simple.
  • the center position of the spherical surface may be changed.
  • the refractive surface is a cylindrical surface or a toric surface, etc., it is a refractive surface created by rotating a line segment around a rotationally symmetric axis different from the optical axis, so the translation of the rotationally symmetric axis and the direction vector of the rotationally symmetric axis are Just tilt it.
  • a spherical surface, a cylindrical surface, and a toric refracting surface can be expressed as a vector equation by determining the respective centers, the rotational symmetry axis, and the rotational radius.
  • the starting position of the light beam, the direction of the light beam, and the intersection are all expressed as vectors.
  • the intersection of the light beam and the refracting surface can be obtained by solving a vector equation by Newton's method or the like.
  • the law of refraction can also be calculated relatively easily using vector equations. These calculations are easy for those skilled in the art. Of course, a method not using a vector equation can also be selected.
  • a rotationally symmetric aspherical surface or a rotationally symmetric diffraction element surface can have the rotationally symmetric axis as an optical axis.
  • the optical axis 1 is used as a coordinate axis, mathematical expression of the refracting surface is facilitated, and it is easy to obtain the refracted ray by obtaining the intersection with the incident ray.
  • a new coordinate system is created based on the optical axis 1 of the deflected refracting surface. Since the expression can be the same as before the deviation, the same calculation formula can be applied.
  • the origin O is set on the anatomical eyeball axis
  • the eyeball axis is taken as the Z axis
  • the coordinate axes X and Y are taken as the coordinate system CS.
  • the coordinate axes X1 and Y1 are determined so that the optical axis 1 that has been displaced with the vertex of the deflected refracting surface as O1 is the Z1 axis and the equation or coordinate component of the refracting surface is the same as the coordinate system CS.
  • a coordinate system CS1 is created.
  • the coordinate system CS1 is related to the coordinate system CS by a transformation matrix representing the parallel movement from the origin O to O1 and the rotation of the coordinate axis.
  • the expression of the refracting surface in the coordinate system CS1 is the same as that in the coordinate system CS, and the intersection can be obtained and the inclination of the refracting surface can be obtained by the same mathematical expression as in the case of no deviation. That is, the starting position INCS of the incident light expressed in the CS coordinate system is converted by a conversion matrix representing translation and rotation of the coordinate system, and the direction INC of the incident light is converted by the conversion matrix of the rotation of the coordinate system, and CS1 The incident light position INCS1 and the incident light direction INC1 displayed in the coordinate system are obtained.
  • intersection point K1 is obtained from INCS1 and INC1 in the CS1 coordinate system.
  • the inclination of the refracting surface at the intersection K1 is obtained, and the inclination REF1 of the refracted ray in the CS1 coordinate system is obtained from the inclination and the incident ray INC1 using the law of refraction.
  • K1 is converted using an inverse matrix of inverse translation and rotation conversion, and REF1 is converted using an inverse matrix of coordinate axis rotation to obtain the intersection K and the direction REF of the refracted ray displayed in the original CS coordinate system. it can.
  • the above method can be applied even when the refracting surface does not have a rotational symmetry axis or a symmetry surface.
  • the refracting surface generally does not have a symmetry axis such as a rotational symmetry axis, and the center of the measurement value, the measurement optical axis, etc.
  • a symmetry axis such as a rotational symmetry axis
  • the anatomical eyeball axis or anatomical corneal axis Generally deviated from the anatomical eyeball axis or anatomical corneal axis.
  • the deviation of the measurement optical axis from the anatomical eye axis and the corneal shape data are stored in the computer as they are, so that the corneal optical axis is the measurement optical axis and the corneal optical axis is displaced from the anatomical eye axis.
  • Optical model can be created in the computer.
  • a refracted light beam can be obtained for the refracting surface having such a deflected corneal optical axis by the same method as described above. If the measurement center of the refracting surface is the origin O1, the corneal optical axis is the Z1 axis, and the X1 and Y1 coordinate axes are selected so that the expression of the original measurement value does not change, a new coordinate system CS1 is created.
  • the starting point and direction of the incident light are converted into the CS1 system, and the intersection of the incident light and the corneal refractive surface and the direction of the refracted light are calculated in the CS1 system. If the position and direction of the refracted ray calculated in the CS1 system is converted into a coordinate system with the anatomical eye axis as the Z axis, the position and direction of the refracted ray in the coordinate system with the anatomical eye axis as the Z axis Is obtained.
  • ray tracing can be performed by deviating not only the cornea but also any surface such as an ophthalmic lens refractive surface or a retina surface.
  • the entire optical unit can be deflected by deflecting each refracting surface without changing the relative position between the refracting surfaces of the optical unit.
  • the image plane corresponding to the retina is curved instead of flat because the actual retina is curved. Otherwise, the image evaluation means cannot be calculated accurately.
  • the intersection of the curved retinal surface and the light beam emitted from the final refractive surface is obtained a plurality of times to obtain the image evaluation means.
  • the position of the retina surface may be changed from 20 mm to about 35 mm according to the actual axial length. Of course, calculations exceeding the above range are possible.
  • the position of the retinal fovea on the image plane is set.
  • the Z axis positive is toward the back of the eyeball, and the X axis is positive on the right In the horizontal direction, the Y axis is positive upward.
  • the radius of curvature of the retina can also be changed to 10 mm or 18 mm, and the amount of deviation of the retinal fovea from the anatomical eyeball axis can be changed accordingly.
  • the axial length is extended. At that time, the eyeball does not expand spherically, but deforms as if the posterior part of the eyeball was pulled backward, so the deviation from the anatomical eyeball axis of the retinal fovea is simply the length of the eyeball It may not be proportional to.
  • the entire eyeball is small, and the deviation of the retinal fovea from the anatomical eyeball axis may become smaller in proportion to the axial length. If there are actual measured values, the radius of curvature of the retina and the position of the central retinal fossa can be calculated using those measured values.
  • the corresponding object point is obtained by tracing back the principal ray from the central retinal fovea toward the center of the final refracting surface or the center of the exit pupil to obtain the object point.
  • a spot diagram on the object plane may be calculated, and the point where the energy distribution is maximized on the spot diagram may be used as the object point.
  • a plurality of ray tracing is performed with respect to the optical system from the object point corresponding to the retinal fovea to obtain the image evaluation means.
  • a two-dimensional array corresponding to the position of the retinal surface is prepared in the computer, and the direction and position of the outgoing light from the object surface are changed.
  • the ray tracing is successively performed to increase the value of the array element corresponding to the intersection of the final outgoing ray with the retina every time the ray arrives.
  • the value of the array element may be increased by 1 for one ray.
  • a value of 20 is assigned to the light beam before diffracting, and a value of 10 is assigned to each light beam after diffracting.
  • a value of 20 is assigned to a ray that reaches the retina without being diffracted, and an array element value corresponding to the intersection of each ray with the retinal surface is increased by the assigned numerical value. good.
  • the numerical value assigned to the one light beam is divided into several light beams such as a diffraction element surface when the object point image evaluation means is obtained, the object image evaluation means is obtained, or the optical system. It can be changed according to refraction.
  • each value of the two-dimensional array element is the energy of light gathered at the retinal position corresponding to the array element.
  • the value is proportional to the amount.
  • a peak where a large amount of light energy is accumulated within about 4 microns in the spot diagram is sufficient for the visual acuity of the human eye to be 1.0 or more, or In daily life, a visual acuity of 0.5 or more is sufficient, and in this case, it is sufficient if there is a peak that collects a large amount of light energy within 8 microns. Therefore, when displaying the spot diagram, a scale should be provided in the display area. This is useful for judgment.
  • the location of the energy peak of the spot diagram can be automatically calculated in the computer, and it can be automatically determined whether or not a certain energy is accumulated around the peak.
  • spot diagram display method there is also a method of simply plotting points corresponding to the intersection coordinates of the ray and the retinal surface on the screen or printed matter without using the two-dimensional array.
  • this method even if a plurality of light rays are incident on the same point on the retinal surface, only one point is plotted, so that the energy of light collected at that point cannot be expressed.
  • a rough energy gathering state can be determined as a simple display method. This method is also used in this specification due to limitations of the drawing format.
  • the image evaluation means in the central retinal area is not limited to a spot diagram on the retinal surface, but optical aberrations such as spherical aberration, astigmatism, coma aberration, etc. of the coaxial optical system, or optical such as MTF and OTF.
  • the transfer function can also be used as an image evaluation.
  • PSF, wavefront aberration, or the like can be used.
  • Seidel aberration theory that can be applied only to a coaxial optical system cannot be strictly applied.
  • the image evaluation means other than these spot diagrams can be compared automatically in the computer, or can be obtained by displaying them and comparing them by a person.
  • the spot diagram of the image evaluation means is not a spot diagram on the retinal plane, but a point in the vicinity including the focal point among the light bundles that converge on the fovea of the retina, and the focal point is separated from the focal point in the light bundle.
  • a spot diagram of the cross section of the ray bundle that converges near the focal point as seen from the side of the direction of ray travel It can also be used. For example, a plane including the principal ray in the light bundle that converges to the focal point is selected, and the intersection of the plane and the light ray in the light bundle is obtained to create a spot diagram.
  • the method according to the present invention can be used to determine the deviation from the anatomical eye axis of at least one refracting surface of the eyeball optical system in order to obtain a clear image in the fovea of the retina.
  • the deviation from which a clear image can be obtained in the fovea of the retina has a certain range. It is also possible to select a deviation near the center within such a deviation range.
  • the displacement of the ophthalmic lens optical unit obtained by the above-described displacement determining method with respect to the anatomical eyeball axis is defined as displacement 1. If the ophthalmic lens supported central axis is mounted or inserted completely coincident with the anatomical eyeball axis, the deviation 1 is the deviation between the ophthalmic lens supported central axis and the ophthalmic lens optical unit. What should I do?
  • the ophthalmic lens optics may deviate 2 instead of deviating 1 with respect to the anatomical eyeball axis.
  • the deviation 1 and the deviation 2 are used to correct the deviation of the ophthalmic lens optical part with respect to the ophthalmic lens supported central axis.
  • the direction in which the retinal fovea deviates from the anatomical eye axis is symmetrical if the left and right eyes have approximately the same anatomical structure. If the ophthalmic lens is inserted by rotating 180 degrees, it can be used for the left eye. In this case, it is sufficient to mark the ophthalmic lens with the direction of deviation of the optical unit so that the insertion direction is not mistaken.
  • a contact lens since the contact lens rotates, it is necessary to devise a technique for avoiding the rotation of the contact lens like the astigmatism correction contact lens. This is not difficult for those skilled in the art.
  • the intraocular lens power can be determined using this method.
  • the intraocular lens power can be obtained by an existing theoretical formula, ray tracing method or regression equation. However, these powers need to be corrected for displaced intraocular lenses.
  • the correction method is as follows. The method determines the optimal optical deflection for the approximate intraocular lens power before correction.
  • the optimal intraocular lens power can be determined by slightly changing the intraocular lens power while maintaining the deviation and calculating image evaluation means such as a spot diagram in the central retina.
  • the anatomical eyeball axis coincides with the corneal optical axis and the corneal shape has a rotationally symmetric axis
  • the specific direction is a positive or negative direction of a perpendicular line drawn from the central axis of the retina to the corneal optical axis, and is substantially horizontal.
  • those skilled in the art can easily apply the present invention when the corneal optical axis does not have a rotationally symmetric axis or when the corneal optical axis does not coincide with the anatomical eyeball axis.
  • the present invention can also be applied to corneal refractive surgery.
  • corneal refraction surgery the cornea is shaved, and at that time, the center of the cornea and the optical axis of the shaved surface are tilted with respect to the anatomical eyeball axis, thereby improving the aberration at the retinal fovea and obtaining a clear image.
  • Those skilled in the art can easily understand that they can be tied.
  • the deviation amount can be obtained by the method disclosed in the present invention.
  • the refractive surface or optical part of the ophthalmic lens deflected with respect to the ophthalmic lens supported central axis has a deviation from the anatomical eyeball axis. It will be. Due to the deviation, a clearer image can be obtained at the fovea of the retina than when the anatomical eyeball axis and the optical axis of the ophthalmic lens optical unit are coaxial.
  • the contact lens of the contact lens by blinking Even when the ophthalmic lens is deviated, such as deviated, a clear image can be maintained in the central retinal fossa.
  • the degree of freedom in designing the ophthalmic lens optical unit can be increased.
  • the spot diagram of the cross section of the ray bundle that converges on the retinal fovea is viewed from the side in the direction in which the ray travels, the depth of focus of the ray bundle that converges on the retinal fovea becomes clear.
  • a more precise determination of the intraocular lens power can be made.
  • the present invention can be applied to power determination and design of a refractive or diffractive bifocal lens or a multifocal ophthalmic lens.
  • astigmatism-like aberration may occur.
  • at least one refractive surface of the intraocular lens optical unit is deviated in a certain direction.
  • the deviation of the optical part of the intraocular lens with respect to the anatomical eyeball axis for reducing the astigmatism of the cornea can be obtained.
  • the deviation at that time is not necessarily a specific deviation.
  • An intraocular lens inserted so that the optical axis of the intraocular lens optical part is deviated from the anatomical eyeball axis.
  • Diagram of a right cylinder defining the intraocular lens supported central axis, the intraocular lens being inserted into the right cylinder.
  • the height from the bottom surface of the right circular cylinder at the portion where the supported portion is in contact with the inner surface of the right circular cylinder is the same.
  • Relationship between object surface, object point, anatomical eye axis, visual axis, and retinal fovea is defined by a straight line connecting the retinal fovea and an object point corresponding to the retinal fovea.
  • deviation of the at least 1 or more refractive surface of an optical system Spherical aberration at the focal point on the anatomical eyeball axis when the optical part aa4 is inserted into the eye.
  • the spherical aberration is zero.
  • the optical part center 12c is taken in a direction perpendicular to the straight line connecting the parts where the supported parts 2a and 2b are in contact with the eye.
  • the optical part center is shifted in the specific direction positive with respect to the intraocular lens supported reference axis, and the optical part optical axis is inclined in the specific direction negative, or the optical part center is shifted in the specific direction negative, so that the optical part optical axis is positive.
  • the optical part center is shifted in the specific direction negative with respect to the intraocular lens supported reference axis and the optical part optical axis is tilted in the specific direction negative, or the optical part center is shifted in the specific direction positive and the optical part optical axis is positive.
  • the optical power ratio between the front and back of the optical unit is 10: 1.
  • FIG. 11 below shows a case where the refractive power ratio between the front surface and the rear surface is changed by bending.
  • a spot diagram in which the optical power ratio between the front surface and the rear surface of the optical unit is 1000: 1.
  • a spot diagram in which the optical power front to back optical power ratio is 2: 1.
  • a spot diagram with a one-to-one refractive power ratio between the front and back of the optical unit A spot diagram in which the refractive power ratio between the front surface and the rear surface of the optical unit is 1: 2. A spot diagram in which the optical power front to back optical power ratio is 0 to 1. A spot diagram in which the refractive power ratio between the front and back of the optical unit is -1 to 10.
  • a retinal fovea in the case where an optical part having a refractive power of 20D is bent and an optical part having a spherical surface of 0 at the focal point on the anatomical eyeball axis with the rear surface being aspherical is deviated from the anatomical eyeball axis. Spot diagram at.
  • the optical power ratio between the front and back of the optical unit is 10: 1.
  • FIG. 12 below shows a case where the refractive power ratio between the front surface and the rear surface is changed by bending.
  • a spot diagram in which the optical power ratio between the front surface and the rear surface of the optical unit is 1000: 1.
  • a spot diagram in which the optical power front to back optical power ratio is 2: 1.
  • a spot diagram in which the refractive power ratio between the front surface and the rear surface of the optical unit is 1: 2.
  • a spot diagram in which the optical power front to back optical power ratio is 0 to 1.
  • a spot diagram in which the refractive power ratio between the front and back of the optical unit is -1 to 10.
  • FIG. 13 below shows a case where the refractive power is changed.
  • a spot diagram when the refractive power is 20D.
  • a spot diagram when the refractive power is 10D.
  • a spot diagram when the refractive power is 5D.
  • a spot diagram when the refractive power is 5D.
  • the display range is changed by shifting the retina position by +0.05 mm.
  • a spot diagram when the refractive power is 0D.
  • FIG. 14 shows a spot diagram when the refractive power is changed.
  • a spot diagram when the refractive power is 20D.
  • a spot diagram when the refractive power is 10D.
  • a spot diagram when the refractive power is 5D.
  • a spot diagram when the refractive power is 0D.
  • Spot diagram when the refractive power is ⁇ 5D.
  • Spot diagram when the refractive power is ⁇ 10D.
  • Spot diagram when the refractive power is ⁇ 10D and the calculation is performed with the retinal fovea position being corrected without being corrected by ⁇ 1.4 mm in a specific direction.
  • the refractive power ratio between the front surface and the back surface is 1: 1, the total power is 20D, the front surface is aspherical, and the spherical aberration coefficient given by the focal point on the anatomical eyeball axis when inserted into the eye.
  • spherical aberration coefficient is -0.1.
  • FIG. 15 shows the spherical aberration when the spherical aberration coefficient is changed.
  • Spherical aberration when spherical aberration coefficient is -0.05.
  • Spherical aberration when the spherical aberration coefficient is -0.02.
  • the refractive power ratio between the front surface and the back surface is 1: 1, the total power is 20D, the front surface is aspherical, and the spherical aberration coefficient given by the focal point on the anatomical eyeball axis when inserted into the eye.
  • the refractive power ratio between the front surface and the back surface is 1000: 1, the total power is 20D, the front surface is aspherical, and the spherical aberration coefficient given by the focal point on the anatomical eyeball axis when inserted into the eye.
  • FIG. 17 shows a spot diagram at the fovea of the retina when the spherical aberration coefficient is changed. Spot diagram when spherical aberration coefficient is -0.05. Spot diagram when spherical aberration coefficient is -0.02. A spot diagram when the spherical aberration coefficient is +0.02. Spot diagram when spherical aberration coefficient is +0.05. A spot diagram when the spherical aberration coefficient is +0.1. The figure of the optical part at the time of deviating only a front surface.
  • the left side of the figure is when the front surface of the biconvex lens is displaced. On the right, the front surface of the convex flat lens is displaced.
  • a spot diagram at the fovea of the retina when only the front surface of the optical part aa4 having a refractive power of 20D and a front-to-back refractive power ratio of 1: 1 is deviated from the anatomical eye axis.
  • the deviation of the vertical and horizontal axes in the figure is the deviation of the front refractive surface in a specific direction with respect to the anatomical eye axis.
  • a spot diagram at the central retinal fret when only the front surface of the optical part aa2 having a refractive power of 20D and a refractive power ratio of the front surface to the rear surface of 1000: 1 is deviated from the anatomical eyeball axis as a front aspheric surface. .
  • the deviation of the vertical and horizontal axes in the figure is the deviation of the front refractive surface.
  • the vertical and horizontal axes in the figure are the deflection of the entire optical unit.
  • the vertical and horizontal axes in the figure are the deflection of the entire optical unit.
  • the refractive power ratio between the front and rear surfaces is 5: 1.
  • FIG. 20 shows a case where the refractive power ratio between the front surface and the rear surface is changed.
  • FIG. 21 shows a spot diagram at the fovea of the retina when the total refractive power is changed.
  • the spot diagram in the retinal fovea when the total refractive power is 20D.
  • the spot diagram in the retinal fovea when the total refractive power is 10D.
  • the spot diagram in the retinal fovea when the total refractive power is 5D.
  • FIG. 21 shows a spot diagram at the fovea of the retina when the total refractive power is changed.
  • the spot diagram in the retinal fovea when the total refractive power is 20D.
  • the spot diagram in the retinal fovea when the total refractive power is 10D.
  • the spot diagram in the retinal fovea when the total refractive power is 5D.
  • the corneal optical axis coincides with the anatomical eye axis
  • the corneal refractive surface is a rotationally symmetric aspherical surface with respect to the corneal optical axis.
  • the design reference axis is the anatomical eye axis.
  • the retinal fovea is assumed to be 1.4 mm horizontally deviated from the anatomical eye axis (design reference axis), and the specific direction is almost the positive and negative direction of the perpendicular line from the retinal fovea to the anatomical eye axis Horizontal direction.
  • the image evaluation means used a spot diagram at the central retinal fossa.
  • the axial length of the retina fovea is about 23.5 mm, in the case of the right eye, it is assumed that it is shifted by 1.4 mm from the anatomical eyeball axis to the horizontal ear side.
  • the position of the retinal fovea was corrected in proportion to the axial length.
  • the deviation from the anatomical eye axis of the retinal fovea is not proportional to the axial length. If the value of the deviation from the anatomical eye axis of the actual central retinal fossa is known, it is easy to calculate using that value.
  • Intraocular lens thickness 0.82mm Pupil depth (distance from front of cornea to pupil) 3.0mm Pupil center position Distance from anatomical eye axis to pupil center 0.0mm in horizontal direction 0.0mm in vertical direction
  • Anterior chamber depth (distance from front of cornea to front of intraocular lens) 3.7mm Air refractive index 1.0 Corneal refractive index 1.375
  • the optimal deviation of the intraocular lens optical unit can be determined by deviating the corneal optical axis as described above.
  • the aspheric intraocular intraocular lens optical unit has zero spherical aberration at the focal point on the corneal optical axis inserted coaxially with the corneal optical axis. A lot of lens optics has been described.
  • the present invention can be applied not only to an intraocular lens optical unit in which spherical aberration is zero, but also to a case where the optical system has various aberrations such as a refractive or diffractive bifocal or a multifocal intraocular lens. .
  • the present invention can also be applied to a case where the cornea has astigmatism (astigmatism), coma aberration, or aberration with no symmetry with respect to the corneal optical axis.
  • Table 1 shows an example of an optical part whose front surface is aspherical.
  • the name of the optical part was given as follows.
  • the first a of aa1 is aspheric which means an aspheric surface
  • the second a is an a of an anterior meaning that the front surface is an aspheric surface.
  • the total refractive power of the optical part is 20D.
  • the spherical aberration is 0 at the focal point on the anatomical eye axis using the method according to Toyohiko Kashiwagi, US Pat. No. 5,191,366 1993.
  • the front surface of the optical unit was aspherical.
  • aa1 is a front convex meniscus lens
  • aa2 is a front convex convex lens
  • aa4 is a biconvex lens.
  • the spherical aberration coefficient has been described in the eighth embodiment.
  • FIG. 4A shows the spherical aberration at the focal point on the anatomical eyeball axis when the optical part aa4 is inserted into the eye with the optical axis 1 of aa4 coaxially with the anatomical eyeball axis.
  • the horizontal axis of FIG. 4a is the vertical spherical aberration, and the vertical axis is the height from the anatomical eye axis when a light ray parallel to the optical axis is incident on the anterior surface of the cornea. As shown, the spherical aberration is zero.
  • FIG. 4B shows a spot diagram in the central retinal fovea when the center of the optical unit aa4 is translated in a specific direction with respect to the anatomical eyeball axis or the optical axis 1 of the optical unit aa4 is tilted in a specific direction. Indicated.
  • the horizontal axis of FIG. 4b represents the inclination of the intraocular lens optical unit in a specific direction in degrees.
  • the horizontal axis positive direction represents that the nose side of the intraocular lens faces forward when the eyeball is viewed from the front.
  • a negative direction indicates that the ear side of the intraocular lens is tilted toward the front.
  • the vertical axis represents the deviation of the center position of the intraocular lens optical unit in a specific direction.
  • the upward direction of the graph is positive, and in the case of the right eye, the center of the optical unit is shifted in the nose direction, and the negative direction is shifted in the ear side. From FIG.
  • this deviation can also be used as a deviation that reduces the aberration in the retinal fovea.
  • FIG. 4d shows a spot diagram in the central retinal fret when the center and inclination of the optical part aa4 are further changed in a negative specific direction. From this figure, for example, it was found that the aberration in the central retinal area is small even when the optical part center position is shifted by 1.3 mm and tilted by -12 degrees. It has been found that if the center of the optical part is shifted in the positive direction, the optical part must be tilted in a more negative direction. This indicates that when the center of the optical part is shifted in a positive specific direction and away from the retinal fovea, the optical axis of the optical part must be directed toward the retinal fovea. However, it does not necessarily match the optical axis of the optical unit with the direction of the central retinal area. In addition, when the deviation of the center of the optical part increases, the aberration increases only with a slight change in tilt.
  • a visual acuity of 1.0 or more corresponds to a resolution of about 4 ⁇ in the central retinal fossa.
  • the eyes are different from photographic lenses, etc. Even if the aberration is large, if the spot diagram has a sharp peak, it can be seen clearly. Therefore, it is good that the spot diagram in the retinal fovea has a sharp peak and a lot of light is collected within about several ⁇ , and the spot diagram has a relatively sharp peak and does not spread to more than about 8 ⁇ . Standard.
  • the actual blur is enlarged by several microns from the spot diagram calculated by the ray tracing method due to the diffraction effect, it is necessary to select an appropriate deviation in consideration of the diffraction effect.
  • Deflection is expressed by a combination of displacement and inclination of the optical part. It will be described as (deviation mm, inclination). For example, (0.1 to 0.6, ⁇ 3 to +3) indicates a near range where the deviation is between 0.1 mm and 0.6 mm and the inclination is ⁇ 3 degrees to 3 degrees.
  • the neighborhood means a neighborhood having a spread equivalent to the size of the deviation or inclination step when the spot diagram is displayed.
  • the range of the deviation that is good on the basis is the vicinity of the area of the following part and the vicinity of the area surrounded by those areas.
  • the allowable range is a region surrounded by the following portions of the region and the vicinity of those regions.
  • region which was not displayed on drawing was also described.
  • the optical unit center may be shifted 0.3 mm from the anatomical eyeball axis in a specific direction on the nasal side, and the inclination may be parallel to the anatomical eyeball axis.
  • the center of the optical part of the intraocular lens may be shifted by 0.3 mm from the center axis of the intraocular lens supported, and the optical axis of the optical part may be made parallel to the center axis of the supported part.
  • a procedure for actually designing such an intraocular lens will be described with reference to FIG.
  • the portions of the intraocular lens supported portions 2a and 2b that are in contact with the eye when they are inserted into the eye are drawn.
  • the intraocular lens supported reference plane is determined from the portions of the intraocular lens supported portions 2a and 2b that are in contact with the eye, and the intraocular lens supported center is determined. 11c and the intraocular lens supported central axis are defined.
  • a right cylindrical surface 13 having a radius of 0.3 mm with the supported central axis 11 as an axis may be formed, and one of arbitrary straight lines parallel to the cylindrical axis on the surface of the right circular cylinder may be used as the optical part optical axis 12.
  • the optical axis of the optical part is the optical axis in the meaning of the optical axis 1, but may be the optical axis in the meaning of the optical axis 2 in general.
  • the optical part center 12c can be moved in the direction of the supported central axis. This travel distance is related to the anterior chamber depth.
  • the intraocular lens optical unit is drawn on the basis of the optical unit center 12c and the optical unit optical axis.
  • the curved part or curved surface part where the supported part is in contact with the eye is extended and connected to the optical part, and the angle and position between the supported part and the optical part are determined from the drawing.
  • Such work can be done by drawing on paper, or by drawing with so-called CAD using a computer. Or it can also design using an enlarged model. If the supported part is elastic and the shape outside the eye and inserted into the eye, the angle of the part where the supported part and the optical part are connected and the shape of the supported part change, It is sufficient to design by estimating the change.
  • reference numeral 17 in FIG. 6a denotes a portion where the intraocular lens is supported in the eye, such as the anterior chamber corner, the capsular equator, and the ciliary groove.
  • intraocular lens supported center 11c in the middle of the portions 2a and 2b where the supported portion is in contact with the eye.
  • the optical part center 12c is on the surface of the cylindrical surface used in the design.
  • a mark in the direction of the center of the optical part with respect to the supported center is indicated by 15. The mark is inserted so as to coincide with a specific direction (in this case, the nasal direction of the right eye).
  • the intraocular lens supported center is inserted.
  • the axis coincides with the anatomical eye axis. If the intraocular lens is inserted so as to satisfy such a condition, 11c is on the anatomical eyeball axis, and the optical part center 12c is offset by 0.3 mm from the support center 11c.
  • the optical axis of the optical part is parallel to the anatomical eye axis and is not tilted.
  • FIG. 6b shows a case where the intraocular lens support portions 2a and 2b are designed so as to be shifted in a direction orthogonal to a straight line connecting the portions in contact with the eye.
  • Reference numeral 11c in FIG. 6b denotes an intraocular lens supported center.
  • the optical part center 12c is above the 11c unlike FIG. 6a, and the mark 15 in the direction of the optical part center is also above.
  • the intraocular lens support is vertically moved, unlike FIG. 6a, but the center of the optical part is displaced 0.3 mm from the anatomical eyeball axis to the nasal side.
  • the optical axis of the optical part is parallel to the anatomical eye axis.
  • the anatomical shape of the iris root of the eye or the lens capsule is not axisymmetric with respect to the anatomical eye axis, or the intraocular lens support reference axis is the anatomical eye axis.
  • the intraocular lens-supported central axis may deviate from the intraocular lens support reference axis or the anatomical eyeball axis due to differences in the insertion method of the operator.
  • FIGS. 7a and 7b show a case where the central axis of the intraocular lens supported and the anatomical eyeball axis coincide with each other. In FIG.
  • the anatomical eyeball axis 8 and the intraocular lens supported central axis 11 pass through the center of the intraocular lens support reference plane 10 and are perpendicular to the plane 10. Therefore, the intraocular lens supported center axis coincides with the anatomical eyeball axis, and the deviation of the optical axis 12 of the intraocular lens optical unit from the supported center axis 11 does not need to be corrected as designed.
  • the intraocular lens support reference plane 10 is inclined as shown in FIG. 7b, the intraocular lens supported central axis 11 is also deviated with respect to the anatomical eyeball axis 8, so It is necessary to correct the deviation of the shaft 12 relative to the intraocular lens supported central shaft 11 from the initial design.
  • the above correction can be performed, for example, as follows.
  • the initial design of the intraocular lens is the same as the actual surgical results, while maintaining the relative positional relationship between the optical part of the intraocular lens and the supported part on the drawing. To deviate. As a result of the displacement, the portion where the supported portion is in contact with the eye is also displaced. Then, only the deviation of the optical unit relative to the anatomical eyeball axis is returned to the initial design deviation.
  • the support portion may be extended from the portion where the supported portion is in contact with the eye to the optical portion and connected to the optical portion to determine the angle and position between the support portion and the optical portion.
  • the intraocular lens support reference axis does not deviate from the anatomical eyeball axis and the intraocular lens supported central axis deviates from the intraocular lens support reference axis due to a surgical error or the like.
  • the deviation of the optical unit with respect to the supported central axis can be corrected.
  • the intraocular lens-supported central axis 11 and the optical part optical axis 12 coincide with each other due to this modification, it is the same as the conventional lens, and is excluded from the claims of the present invention.
  • the design method of the connecting part between the intraocular lens optical part and the supported part is not limited to only two intraocular lenses, but the supported parts are three, four or more supported parts. Is a circular shape or a substantially circular shape, or even when the supported part is in contact with a surface instead of a line in the eye, the intraocular lens support reference plane, support reference axis, supported center, supported center axis Using this concept, those skilled in the art can design in the same way.
  • Table 2 (Relationship with pupil center, intraocular lens optical axis, visual axis)
  • Table 2 the distance in the specific direction between the visual axis on the pupil plane and the pupil center is shown corresponding to FIG. 4b.
  • the number at the left end of Table 1 is the deviation from the anatomical eye axis at the center of the intraocular lens optical unit, and the number at the lower end is the inclination of the intraocular lens optical unit with respect to the anatomical eye axis.
  • the numbers on the vertical and horizontal axes correspond to the vertical and horizontal axes in FIG.
  • Table 3 the angle between the visual axis and the optical axis of the intraocular lens is shown in Table 3 corresponding to FIG.
  • the meanings of the vertical and horizontal axes are the same as in Table 2.
  • the aberration at the retinal fovea is minimized when the deviation is (0.3, 0.0).
  • the center of the optical part is shifted by 0.3 mm from the anatomical eyeball axis.
  • the optical part optical axis is parallel to the anatomical eyeball axis and is shifted by 0.3 mm from the anatomical eyeball axis.
  • the pupil center is now on the anatomical eye axis, the optical axis of the optical part never overlaps the pupil center.
  • the visual axis is shifted by 0.43 mm in the specific direction from the center of the pupil on the pupil plane.
  • the angle between the visual axis when the aberration at the retinal fovea is minimized (0.3, 0.0) and the optical axis of the intraocular lens optical unit is 5.22 degrees.
  • the axis and the optical axis of the intraocular lens optical unit are not parallel, and the visual axis and the optical axis of the intraocular lens optical unit do not coincide with each other.
  • the patent document 1 claims that the optical axis of the intraocular lens optical unit is made to coincide with the center of the pupil, or is made to be parallel or coincident with the visual axis. This claim is neither necessary nor sufficient to minimize aberrations in the central retinal fossa.
  • Patent Document 1 is not a claim obtained at all for the purpose of reducing the aberration in the central retinal fossa.
  • Example 2 the spot diagram in the central retinal fret when the optical part aa2 of Table 1 is displaced in the same manner as in Example 1 is shown in FIG.
  • the range in which the aberration at the retinal fovea of the optical part aa2 is good is the following area and the vicinity of the area surrounded by these areas.
  • the notation is the same as in Example 1.
  • the allowable range is the following region and the vicinity of the region surrounded by these regions (0.4 to 0.8, ⁇ 12 to 0) (0.9, ⁇ 12 to ⁇ 8, and ⁇ 2 to 0) ( 1.0, -14 to -12 and -2 to 0) In addition to the above range, there are good and acceptable ranges even when the deviation is 1.0 mm or more. However, when the deviation is 1.0 mm or more, the range of the tilt where the aberration is possible becomes narrow.
  • the center of the optical part is set to the anatomical eye axis. It is better to design the optical part to tilt -5 degrees by shifting 0.7mm in a specific direction.
  • the center of the optical unit may be tilted 0.7 mm in the positive specific direction from the anatomical eyeball axis, and the tilt is ⁇ 5 degrees in the specific direction, that is, the ear side of the intraocular lens may be in front.
  • a procedure for actually designing an intraocular lens having the optical part aa2 will be described with reference to FIG.
  • the supported reference plane 10 As described in the definition of the intraocular lens supported reference axis, the supported reference plane 10, the supported center 11c, and the supported central axis 11 are determined from the portions 2a and 2b in FIG.
  • a circle having a radius of 0.7 mm is drawn in the supported reference plane with the supported center as the center. With this circle as the bottom surface, a cone 14 having a vertex on the retina side on the supported central axis 11 and an apex angle of 10 degrees, which is a double of 5 degrees, is formed.
  • the cone can be moved in the direction of the arrow parallel to the supported central axis 11, and the movement in the direction of the arrow determines the anterior chamber depth when the lens is inserted into the eye.
  • An arbitrary point on the circumference of the cone bottom surface may be the optical part center 12c, and a straight line connecting the point 12c and the apex of the cone may be the optical part optical axis 12.
  • the optical part is drawn based on the center of the optical part and the optical axis. Then, the curved portion or curved surface portion in contact with the eye of the supported portion is extended and connected to the optical portion for drawing, and the angle and position where the supported portion and the optical portion are connected are determined.
  • Such work can be done by drawing on paper, or by drawing with so-called CAD using a computer. Or it can design using an enlarged model. If the supported part is elastic and the shape outside the eye and inserted into the eye, the angle of the part where the supported part and the optical part are connected and the shape of the supported part change, It is sufficient to design by estimating the change.
  • the lens designed in this way is rotated 180 degrees around the supported reference axis, the center of the optical part is shifted in the negative direction of the specific direction and becomes an intraocular lens inclined in the positive direction, and the left and right eyes should be symmetric. Can be inserted into other eyes.
  • the position of the mark may be in a specific direction in which the center of the optical part is shifted, or it is better to keep the position on the ear side or the nose side constant so that the operator can easily understand.
  • the anatomical shape of the iris root of the eye or the lens capsule is not completely axisymmetric with respect to the anatomical eye axis, or due to differences in the insertion method of the surgeon, etc.
  • the support portion changes in the lens capsule or the part in contact with the inside of the eye, and the supported central axis is displaced from the anatomical eyeball axis. In such a case, if the displacement is constant to some extent, it can be corrected in the same manner as in the first embodiment.
  • FIG. 9b shows a design procedure when the optical unit center position is shifted in the negative specific direction and the optical unit is tilted in the negative specific direction.
  • the apex of the cone is on the cornea side.
  • the intraocular lens designed in this way is rotated 180 degrees around the supported central axis, the center position of the optical unit is shifted in the positive direction and the lens tilts in the positive direction. Can be inserted into other eyes.
  • the marking and the like for clearly indicating the specific direction is the same as in the above embodiment.
  • the intraocular lens-supported central axis is used as the axis
  • the vertex is the intraocular lens Create a cone that is on the supported central axis and whose apex angle is twice the inclination to be deviated, with the vertex of the cone as the center of the intraocular lens optical part, and an arbitrary straight line passing through the vertex and on the side of the cone What is necessary is just to design as an optical axis of an intraocular lens optical part.
  • optical unit optical axis An arbitrary straight line that rides on the side surface of a cylinder or a cone that defines the optical axis of the optical unit described in the first or second embodiment can be used as the optical unit optical axis.
  • the relative positional relationship between the intraocular lens supported portion and the optical portion optical axis changes depending on the straight line and the selection method, but the relative positional relationship between the intraocular lens supported central axis and the optical portion optical axis depends on the intraocular lens supported portion. It does not change except for the rotation of the support portion around the supported central axis.
  • the intraocular lens when inserting the intraocular lens, if the intraocular lens is inserted by rotating around the supported central axis, the deviation of the optical axis of the intraocular lens optical unit from the anatomical eyeball axis is selected. Regardless of whether they are the same.
  • the intraocular lens optical unit is made of two refractive surfaces and the entire optical unit is displaced as a whole has been described.
  • only one refracting surface of the intraocular lens optical unit is deflected as in the embodiments described later, only one refracting surface is centered on the optical unit center in the same manner. It is possible to design an intraocular lens optical unit in which the refractive surface is deviated.
  • Example 3 the case where the front surface of the intraocular lens is a flat surface and the rear surface is convex is shown.
  • an optical unit in which the spherical aberration is zero at the focal point on the anatomical eyeball axis by using the method of Toyohiko Kashiwagi ap6 was designed.
  • the characteristics of the optical part ap6 are shown in Table 4 below.
  • the optical part ap6 has an optical axis, and the optical axis is deviated with respect to the anatomical eyeball axis, and FIG. 10 shows a part of the spot diagram in the central retinal fret.
  • the deviation with good aberration in the central retinal fossa is in the vicinity of the area of the following part and the vicinity area surrounded by those areas.
  • the notation is the same as in the first embodiment.
  • the areas that were implemented but not shown are also listed.
  • the optical axis of the intraocular lens optical unit may be designed to have a deviation of 0.3 mm and an inclination of ⁇ 2 degrees with respect to the intraocular lens supported central axis. Also, when it is found that the central axis supported by the intraocular lens is displaced with respect to the anatomical eyeball axis when the operation is actually performed, the optical part light is also obtained in the same manner as in the first and second embodiments. What is necessary is just to correct
  • FIG. 11-aa1 and 11-aa2 have front-side convex meniscus lenses and convex flat lenses that have a good or good spot diagram over a wide range of optical parts, and also have rear-surface convex shapes such as FIGS. 11-aa6 and 11-aa7.
  • a plano-convex lens or a meniscus lens has a small range of deviation where the aberration is good or acceptable.
  • the front-rear surface has a refractive power ratio of 1: 1, which is the middle, and among the biconvex lenses, the optical unit whose front surface has a larger refractive power than the rear surface has a wide range of deviation.
  • the spot diagram has a sharp peak.
  • the spot diagram has a large peak over a certain range of deviation, select a deviation near the center of the range and design the optic to have that deviation. Even if the lens optical unit is deviated, an increase in aberrations at the retinal fovea can be reduced.
  • An optical part with a front convex meniscus, a convex flat lens, or a biconvex lens with a refractive power of the front surface larger than the refractive power of the rear surface is larger than a convex meniscus lens or plano-convex lens of the rear surface or a biconvex lens with a larger refractive power of the rear surface.
  • the spot diagram has a wide range of peaks.
  • the bending where the former spot diagram has a wide range with a large peak can be said to be a bending that is not easily affected by surgical errors.
  • the spot diagram has a narrow peak range but can be used if the surgical accuracy is high.
  • FIG. 12-ap1 to FIG. 12-ap7 show spot diagrams at the retinal fovea when the optical part is displaced with respect to the anatomical eyeball axis, assuming that the lens of Table 4 is inserted into the eye. Indicated. From these results, if the refractive power of the front surface and the rear surface is the same ratio, the range of the deviation where the spot diagram in the retinal fovea has a large peak is whether the front surface is aspherical or the rear surface is aspherical. A similar trend was shown. Therefore, there is no significant effect on the deviation with a peak in the spot diagram depending on whether the front or rear surface is aspherical.
  • the optical part in which the refractive power ratio of the front surface and the rear surface is 1: 1 and the refractive power of the entire optical unit is changed to 30D, 20D, 10D, 5D, 0D, ⁇ 5D, ⁇ 10D is defined as the anatomical eyeball axis.
  • aa4p30 to aa4p-10 were designed so that the spherical aberration would be zero at the focal point on the anatomical eyeball axis by the method of Kashiwagi.
  • the characteristics of each optical part are shown in Table 5.
  • the first a is aspheric (aspheric)
  • the second a is an anterior (front surface)
  • 4 is the fourth of the bending, that is, the ratio of the refractive power of the front surface to the rear surface is 1: 1
  • p Is an acronym for power (refractive power)
  • the subsequent number is refractive power.
  • the focal length changes and the corresponding axial length also changes.
  • the radius of curvature of the retina also changes.
  • half the length of the axial axis is defined as the radius of curvature of the retina.
  • the retinal fovea position was calculated to be shifted by 1.4 mm in a specific direction when the axial length was 23 mm, but the shift was calculated in proportion to the axial length.
  • an optical model is created in the computer using these values, and calculation and design suitable for the case can be performed.
  • FIG. 13-aa4p-10 show spot diagrams in the central retinal fret when each of the above lenses is displaced with respect to the anatomical eye axis. Further, FIG. 13-aa4p-10b shows a spot diagram in which the position of the retinal fovea is not corrected by the optical unit aa4p-10 and is left shifted by ⁇ 1.4 mm in a specific direction from the anatomical eyeball axis.
  • the magnitude of the refractive power is also an important factor for determining the optimum deviation of the optical part.
  • the refractive power of the optical unit is 0, the optical unit has only an aberration correcting function, but even in the case of such an aberration correcting lens, the aberration becomes the smallest with a deviation of (0.6, 4). Deviated effect comes out.
  • the retinal fovea position was calculated on the assumption that the deviation from the anatomical eyeball axis was increased in proportion to the eyeball length.
  • the axial length is about 38 mm and strong axial myopia. If the retinal foveal position changes in proportion to the axial length, the retinal foveal position is about -2.3 mm. It is corrected. However, in the case of axial myopia, the retinal fovea position often does not change significantly.
  • FIG. 13-aa4p-10b shows a spot diagram when the lens power is ⁇ 10 diopter, the axial length is about 38 mm, and the retinal foveal position is kept at ⁇ 1.4 mm.
  • FIG. 13-aa4p-10 and FIG. 13-aa4p-10b have the same deviation range for comparison. Comparing the two figures, it can be seen that the spot diagram changes greatly due to the difference in the fovea position. Therefore, the central retinal position is also an important factor in determining the optimum optical part deviation. If the actual retinal fovea position is known, the value can be used to determine the optimum deviation.
  • FIG. 14-aa2p30 to FIG. 14-aa2p-10 show spot diagrams at the retinal fovea when each of these optical parts is displaced with respect to the anatomical eyeball axis.
  • FIG. 14-aa2p-10b shows a spot diagram in which the position of the retinal fovea is not corrected by the optical unit aa2p-10 but is shifted by -1.4 mm in a specific direction from the anatomical eyeball axis.
  • the range or value of the deviation that is the minimum or good aberration at the central retinal fossa is, for example, the following region and the vicinity of the region.
  • the description is the same as in the first embodiment.
  • (1.0, -13) (0.9, -12 to -5) (0.8, -11 to -6) (0.7, -10 to -7) at a refractive power of 30D (09, -1 to 1) (0.8, -1 to 1) (0.7, -4 to 1) (0.6, -3 to -1) at a refractive power of 20D
  • Refractive power is 10D (0.7, 2-5) (0.6, 1-4) (0.5, 0-3)
  • Refractive power is 0D (0.7, -6 to 1) (0.6, -6 to 2), (0.7, -4 to -2) (0.6, -6 to -4) (0.5, -7) (0.4, -9) at -5D (0.7, -3) (0.6,
  • the center position of the optical part where the aberration is minimum or good is 0.4 to 1.0 mm. Further, for each refractive power, the aberration at the central retinal area is reduced over a range of deviation wider than the optical part aa4 having a refractive power of 1: 1 on the front and rear surfaces.
  • the convex lens has a strong effect of limiting an increase in aberrations in the central retinal area when the optical part is displaced due to a surgical error or the like.
  • the aberration in the central retinal area is reduced in a relatively wide range with respect to the different refracting power of the optical part.
  • the refractive power of the rear surface of the biconvex lens becomes larger than that of the front surface, the range of deviation where the aberration is reduced becomes narrow, but it can be used if the surgical accuracy is high.
  • the retinal fovea position was calculated on the assumption that the deviation from the anatomical eye axis increased in proportion to the eye axis length.
  • the eye axis length is about 38 mm
  • the retinal fovea position is corrected to about -2.3 mm.
  • FIG. 14-aa2p-10b shows a spot diagram when the intraocular lens power is ⁇ 10 diopter
  • the axial length is about 38 mm
  • the retinal foveal position is not changed to ⁇ 1.4 mm.
  • 14-aa2p-10 and FIG. 14-aa2p-10b have the same displacement range for comparison.
  • the spot diagram changes greatly due to the difference in the fovea position. Therefore, the retinal fovea position is also an important factor in determining the optimum deviation range. If the actual retinal fovea position is known, the value can be used to determine the optimum deviation.
  • Examples 1 to 7 show optical parts in which spherical aberration is zero on the anatomical eye axis. This is because the effect when the optical part is displaced is clearer when the spherical aberration is zero. However, the effect of deflecting the optical part occurs even if the spherical aberration is not zero. Therefore, in Example 8, the spherical aberration is changed for the optical part where the spherical aberration is not zero at the focal point on the anatomical eye axis, and the relationship between the deviation of the optical part and the central axis of the retina is shown.
  • Spherical aberration is the distance SA from the paraxial image point at the position where a ray incident in parallel to the anatomical eye axis at a height y (mm) at the front surface of the cornea has the optical axis of the intraocular lens coaxial with the cornea.
  • (mm) SA C * y * y
  • C the aberration coefficient The case where it is expressed is shown.
  • C the spherical aberration is 0, which corresponds to Examples 1 to 7.
  • the refractive power ratio of the optical part is 20D, the refractive power ratio between the front and back of the optical part is 1: 1, and it is assumed that the optical part is inserted into the eye coaxially with the anatomical eyeball axis.
  • the front surface of the intraocular lens is made an aspheric surface by the above-mentioned method so as to have spherical aberration with C set to -0.1, -0.05, -0.02, 0.02, 0.05, 0.1.
  • Optical part aa4sam. 1, aa4sam. 05, aa4sam. 02, aa4sap. 02: aa4sap. 05, aa4sap. 1 was designed.
  • the characteristics of each lens are shown in Table 7.
  • aa4 of aa4sam has an aspheric front surface corresponding to the optical part aa4, and the front-rear refractive power ratio represents 1: 1.
  • sa of sam represents spherical aberration spherical aberration
  • m represents a minus code
  • p represents a plus code.
  • FIG. 16-aa4spm spot diagram of the retinal fovea when the optical part of Table 7 is displaced with respect to the anatomical eyeball axis. 1 to FIG. 16-aa4spp. It was shown in 1.
  • the spherical aberration with the spherical aberration coefficient of ⁇ 0.1 is almost equal to the spherical aberration in the case of the biconvex spherical lens, and the spherical aberration is large. Since spherical aberration is large, FIG. 16-aa4spm.
  • the spot diagram has a sharp peak in a wide deviation range.
  • FIG. 16-aa4spp With an aberration coefficient of +02 of 02, the light is well integrated at the deviation (0.3, 0), which coincides with the deviation that minimizes the aberration in the case of the optical part aa4 where the spherical aberration is zero.
  • the spot diagram has a sharp peak in a wide range when the aberration coefficient is large, in common with the case where the aberration coefficient is negative.
  • the aberration becomes small when the center of the optical part is positive and the inclination of the optical part is negative.
  • the spherical aberration coefficient is positive, the aberration decreases when the deviation is in the vicinity of (0.3, -6 to 0). Therefore, it is good to design to have this deviation.
  • the magnitude of the spherical aberration on the optical axis varies, and may be positive or negative. Even in such a case, if a common deviation is selected so that the aberration does not increase regardless of changes in spherical aberration, and the optical part is designed to have that deviation, the cornea with different spherical aberration can be used. It is possible to design an intraocular lens with little aberration in the central retinal fossa. For example, when the refractive power ratio between the front surface and the rear surface, which is the lens in Table 7, is 1: 1, the displacement is good near (0.3, -3 to 0). In addition, when combining positive and negative spherical aberrations in a bifocal or multifocal optical unit, it is easily estimated that there is an optimal deviation of the optical unit. It can be obtained using.
  • the center of the deviation range having a sharp peak in the spot diagram is not (0, 0). If it is designed to have a deviation at the center of these deviation ranges, even if the optical part is displaced due to a surgical error, the deviation resulting from the deviation is a deviation range having a peak peak on the spot diagram. Since it stays, an increase in aberration can be prevented. If the spherical aberration is small, the deviation range where the aberration is small is narrow, so that high accuracy is required for the operation. Therefore, it is preferable to change the spherical aberration in consideration of the operation accuracy.
  • the spherical aberration coefficient of the front convex convex lens is changed as in the eighth embodiment.
  • the spherical aberration coefficient C is -0.1 at the focal point on the anatomical eye axis.
  • the optical part aa2sam. Is made aspherical on the front surface by the above-mentioned method so as to have spherical aberrations of -0.05, -0.02, 0.02, 0.05, 0.1. 1 to aa2sap.
  • Table 8 shows a list of optical parts designed in this way. For each lens in Table 8, the change of the spot diagram at the fovea of the retina is shown in Fig. 17-aa2spm. 1 to FIG. 17-aa2spp. It was shown in 1.
  • the spot diagram has a broad peak in a wide range. Further, when the spherical aberration is reduced, the range where the spot diagram has a large peak approaches the case of the spherical aberration of zero. It was also found that it is a property common to biconvex lenses that the center of the optical part is positive when the spherical aberration coefficient is positive and the spot diagram has a sharp peak when the inclination is negative.
  • Examples 8 and 9 only the case where the spherical aberration can be expressed by a quadratic function is shown. However, there is an optimum optical part deviation not only for the quadratic function but also for any spherical aberration (aperture aberration). You can easily guess what to do. If the method according to the present invention is used for an optical part having such an arbitrary spherical aberration, it is possible to determine the deviation of the optical part that reduces the aberration at the central retina. For example, a refractive or diffractive bifocal lens or a multifocal lens intentionally increases the depth of focus by designing an optical unit that has positive or negative spherical aberration (aperture aberration).
  • the retinal fovea is located on the anatomical eye axis, or the design reference axis and the intraocular lens support reference are shifted from the anatomical eye axis. Since there is an error that the axes (anatomical eyeball axes) coincide with each other, the performance of the original optical unit cannot be exhibited. Therefore, the method of the present invention can be applied to those lenses. In other words, the optical axis of the bifocal or multifocal lens is offset with respect to the anatomical eye axis, and the spot diagram at the fovea of the retina is calculated. Deviation can be defined.
  • the optimum deviation varies depending on the bending of the optical part, the total refractive power, the position of the central retinal fossa, and the like.
  • the explanation has been made assuming that the aberration due to the cornea is only spherical aberration (aperture aberration), but the present invention is also applied to the case where the aberration due to the cornea is astigmatism or astigmatism. it can.
  • the aberration due to the cornea is astigmatism
  • an astigmatism correcting intraocular lens is inserted for correction.
  • the aberration at the retinal fovea is small when the astigmatism correcting lens optical unit is deviated from the anatomical eyeball axis.
  • the intraocular lens optical unit can be similarly deviated from the anatomical eyeball axis to reduce the aberration at the retinal fovea.
  • the aberration at the retinal fovea can be reduced by deviating the optical part. It is rather natural.
  • the corneal optical axis is selected so that the retinal fovea is on the corneal optical axis and the corneal optical axis is the optical axis 1, the intraocular lens optical axis 1 is coaxial with the corneal optical axis 1.
  • the cornea, the intraocular lens, and the retinal fovea are completely a coaxial optical system, and aberrations at the retinal fovea can be reduced.
  • the corneal optical axis 1 is deviated from the anatomical eyeball axis
  • the optical axis of the intraocular lens optical unit is also deviated from the anatomical eyeball axis and falls within the scope of the present invention.
  • the spot diagram in the central retinal fret has a peak that is displaced with respect to the anatomical eyeball axis,
  • the intraocular lens optical axis is deviated due to a surgical error, it is possible to limit an increase in aberration in the retinal fovea.
  • the amount by which the intraocular lens optical unit is displaced includes the corneal refractive power, the aberration due to the cornea, the refractive power ratio bending of the front and rear surfaces of the intraocular lens optical unit, the aberration of the optical system, the axial length,
  • the refractive power ratio or the retinal fovea varies depending on the amount of deviation from the anatomical eye axis, the optimum deviation can be determined by the present invention.
  • FIG. 18B shows the change of the spot diagram at the central retinal fret when only the front surface of the optical part aa4 is variously displaced with respect to the anatomical eyeball axis.
  • FIG. 18b for example, when the refractive surface center of the front surface of the optical unit is shifted by 0.3 mm and the inclination is in the range of ⁇ 4 to 4 degrees, the spot diagram in the central retinal fret has a sharp peak.
  • FIG. 18b shows the change of the spot diagram at the central retinal fret when only the front surface of the optical part aa4 is variously displaced with respect to the anatomical eyeball axis.
  • FIG. 18c shows a case where only the front surface of the optical part aa2 is displaced.
  • the center of the refractive surface of the front surface of the optical part aa2 is shifted by 0.6 mm and tilted by ⁇ 1 degree from ⁇ 7, the aberration at the retinal fovea can be reduced.
  • the spot diagram in the central retinal fret also has a sharp peak by deviating a part of the refractive surface of the optical part in this way.
  • FIG. 19A shows a spot diagram at the center of the retina when the center of the front surface of the optical unit aa4 is shifted in a specific direction by 0.3 mm with respect to the rear surface and then the entire optical unit is displaced.
  • the center of the optical unit in FIG. 19a is a point from the cornea at a distance of half the intraocular lens thickness from the apex of the rear surface on the anatomical eyeball axis before the front surface is shifted. From FIG. 19a, the deviation of the optical part is almost zero, such as (0.0, ⁇ 1 to 0), that is, the whole optical part is not deviated, and the spot diagram in the central retina has a sharp peak. Can be made.
  • FIG. 19b shows a spot diagram at the retinal fovea when the entire optical part is displaced. From FIG. 19b, it is possible to minimize the aberration at the retinal fovea without changing the deviation (0.0, 0.0), that is, the entire optical part, and to have a peak in the spot diagram. Thus, if the front surface is deviated from the rear surface in advance, the aberration can be reduced without deviating the entire optical unit. In addition to the above, assuming that the front surface is shifted and inclined with respect to the rear surface, the aberration can be reduced by deviating the entire optical unit.
  • Table 9 shows the characteristics of the spherical lens used.
  • the spherical lens has a sharp peak in the spot diagram at the central retinal area in a wide range as compared with an aspherical optical unit in which the aberration is zero or small.
  • the center of the deviation range where the aberration is good is not (0.0, 0.0).
  • the optical part is held with respect to the central axis supported by the intraocular lens, the optical part is deflected by surgery.
  • the increase in aberration can be limited even if it is shifted.
  • the aberration due to the cornea varies among individuals, the aberration when a spherical lens is inserted is different, and the spot diagram shown in FIG. 20 also changes.
  • the optimal deviation of the spherical lens optical unit can be obtained by the present invention. Can be determined.
  • the range where the aberration is good is approximately the following regions and the vicinity of the regions surrounded by these regions.
  • the notation is the same as in Example 1.
  • the range that was actually implemented but not displayed in the figure is also described.
  • the range of deviation in which aberration is possible is approximately the following regions and regions surrounded by these regions.
  • the vicinity of ( ⁇ 0.4, ⁇ 3) can be selected as the center of the deviation with good aberration. If the optical part optical axis has its deviation with respect to the intraocular lens supported central axis, even if the intraocular lens supported central axis is deviated due to a surgical error, the optical part deviation has an aberration. Since it is within the range of good deviation, an increase in aberration can be prevented. Of course, other deviations can be selected depending on the skill of the operation.
  • the range in which the aberration is good is roughly the vicinity of the following region and the region surrounded by the region as shown in FIG. 20-s5.
  • deviations that were implemented but not shown in FIG. 20 were also included.
  • the range in which the spot diagram is good as shown in FIG. 20-s7 is approximately the following region and the region surrounded by the regions.
  • deviations that were implemented but not shown in FIG. 20 were also included.
  • a front convex meniscus lens, a convex flat lens, or a biconvex lens having a larger refractive power on the front surface than the rear surface If the inclination of the optical part is constant in the range of about 6 to 0 degrees, it can be seen that even if the vertical direction of the figure, that is, the center of the optical part is deviated, the spot diagram has a deep peak in the retinal fovea.
  • a lens having a refractive power on the front surface larger than the rear surface is strong against an optical center position shift
  • a lens having a refractive power on the rear surface larger than the front surface is strong against tilt.
  • Example 13 the refractive power of the optical part in which the front surface and the rear surface are both spherical and the ratio of the refractive power of the front surface to the rear surface is 1: 1 is 30D, 20D, 10D, 5D, 0D, -5D "-10D.
  • FIG. 21-s4p30 to FIG. 21-s4p-10 show the case where the optical part is deflected by changing the above. Table 10 shows the characteristics of these optical parts.
  • FIG. 21-s2p30 to FIG. 21-s2p-10 show cases where the refractive power ratio between the front surface and the rear surface is 1000: 1.
  • Table 11 shows the characteristics of these optical parts. As shown in FIG.
  • the larger the refractive power the smaller the range where the spot diagram in the retinal fovea has a large peak. .
  • the range becomes wide.
  • the refractive power is 0, unlike the non-aberration aspherical optical part, the spot diagram hardly changes even if it is deviated.
  • the refractive power is large, the deviation of the spot diagram having a sharp peak is in a negative direction, but moves in a positive direction as the refractive power decreases.
  • the lens has a negative refractive power, the inclination becomes negative again.
  • the axial length is about 38 mm and the retinal fovea is shifted by -2.3 mm.
  • the position of the retinal fovea is considered not to deviate so much. Therefore, the calculation with the position of the central retinal fossa being ⁇ 1.4 mm is shown in FIG. 21-s4p-10b and FIG. 21-s2p-10b.
  • the spot diagram changes greatly due to the difference in the position of the central retinal fret, and the optimum deviation of the optical part also changes. Therefore, the magnitude of the deviation of the retinal fovea position from the anatomical eyeball axis is also a large factor affecting the aberration in the retinal fovea. If the actual position of the retinal fovea is known, the value can be used to determine the optimum deviation using the method of the present invention.
  • the pupil position is on the anatomical eyeball axis.
  • the pupil position is often displaced substantially in the horizontal direction.
  • the deviation is 0. It is about several mm. Therefore, in the case where the pupil positions are shifted by ⁇ 0.6 mm, 0.0 mm, and +0.6 mm respectively in the horizontal direction, the optical part aa4 is displaced from the anatomical eye axis at the central axis of the retina.
  • the changes in the spot diagram are shown in FIGS. 22a, 22b and 22c.
  • Deviations that minimize the aberrations at the central retinal fret are not significantly changed to (0.3,1), (0.3,0), and (0.3,0), respectively, but in the vicinity of the deviation Aberrations at different deflections are different. Therefore, when the pupil position is extremely deviated, it is necessary to obtain the optimum deviation of the intraocular lens in consideration of the deviation of the pupil position from the anatomical eyeball axis. For example, when the pupil center is shifted by 0.6 mm positive in the horizontal direction, the intraocular lens is displaced due to a surgical error by setting the deviation of the optical part to (0.4 to 0.5, 0). In some cases, an increase in aberrations can be reduced.
  • the intraocular lens optical unit has a spherical surface, aspheric surface, front / rear refractive power ratio, overall refractive power, deviation of only the front / rear surface, a lens whose center of the front / rear surface is shifted, and pupil position is deviated. Examples are shown for cases where there are cases.
  • the present invention provides an optimal optical part displacement for deviations to other than the above, for example, vertical deviations, different axial lengths, different deviations from the anatomical eye axis of the retinal fovea, etc. It can be determined by using.
  • refractive and diffractive bifocal and multifocal lenses are currently designed to be symmetric with respect to the optical axis, but by displacing at least one refractive surface thereof with respect to the anatomical eye axis, The performance in the retinal fovea deviated from the anatomical eye axis of the optical part can be sufficiently exhibited. The optimum deviation can be obtained and created by the method of the present invention.
  • a material for producing an intraocular lens designed by the method of the present invention a material such as acrylic, HEMA, or silicon can be used.
  • the supported part may be the same material as those, or may be another material such as polypropylene. It is also possible to create using a shape memory material.

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Abstract

L'invention porte sur une lentille ophtalmique qui surmonte les défauts d'un procédé classique de conception de lentille ophtalmique, qui ne prend pas en considération la déviation de la fovéa centralis de la rétine par rapport à l'axe oculaire anatomique, et qui crée une image nette au niveau de la fovéa centralis de la rétine ou maintient une image nette au niveau de la fovéa centralis de la rétine, même si une composante optique est déviée en raison d'une opération ou similaire. L'invention porte également sur un dispositif d'opération de correction de réfraction de cornée qui crée une image nette au niveau de la fovéa centralis de la rétine. Un procédé de conception d'une lentille ophtalmique ou d'une opération de correction de réfraction de cornée comprend la création d'un modèle mathématique d'un système optique de globe oculaire dans un ordinateur, l'évaluation d'une image au niveau de la fovéa centralis de la rétine tout en déviant la surface de réfraction du système optique, et l'obtention d'une déviation optimale par la surface de réfraction. La lentille ophtalmique est caractérisée en ce que la surface de réfraction du composant optique de la lentille ophtalmique est réglée pour présenter une déviation par rapport à l'axe central sur lequel une lentille ophtalmique est portée, de telle sorte que la composante optique de la lentille ophtalmique est déviée par rapport à l'axe oculaire anatomique. Un procédé de conception d'opération de correction de réfraction de cornée et un dispositif d'opération de correction de réfraction de cornée selon l’invention sont caractérisés en ce que la surface de réfraction devant être déformée dans une opération de correction de réfraction de cornée est déviée par rapport à l'axe oculaire anatomique.
PCT/JP2008/003582 2008-12-03 2008-12-03 Procédé de conception de lentille ophtalmique, lentille ophtalmique et dispositif d'opération de correction de réfraction WO2010064278A1 (fr)

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Cited By (3)

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WO2012137748A1 (fr) * 2011-04-05 2012-10-11 興和株式会社 Méthode de conception de lentilles intraoculaires et lentille intraoculaire
WO2015136997A1 (fr) * 2014-03-11 2015-09-17 興和株式会社 Lentille ophtalmique et procédé de conception de lentille ophtalmique
US10765842B2 (en) 2011-07-14 2020-09-08 W. L. Gore & Associates, Inc. Expandable medical devices

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Cited By (8)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
WO2012137748A1 (fr) * 2011-04-05 2012-10-11 興和株式会社 Méthode de conception de lentilles intraoculaires et lentille intraoculaire
CN103501729A (zh) * 2011-04-05 2014-01-08 兴和株式会社 眼内透镜设计方法以及眼内透镜
US9463088B2 (en) 2011-04-05 2016-10-11 Kowa Company, Ltd. Intraocular lens design method and intraocular lens
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US10765842B2 (en) 2011-07-14 2020-09-08 W. L. Gore & Associates, Inc. Expandable medical devices
US11786709B2 (en) 2011-07-14 2023-10-17 W. L. Gore & Associates, Inc. Expandable medical devices
WO2015136997A1 (fr) * 2014-03-11 2015-09-17 興和株式会社 Lentille ophtalmique et procédé de conception de lentille ophtalmique
JP6049939B2 (ja) * 2014-03-11 2016-12-27 興和株式会社 眼用レンズ及び眼用レンズの設計方法

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