WO2004099858A1 - Lentille de contact avec hydrogel et methode de correction pour aberrations d'ordre eleve de la vue - Google Patents

Lentille de contact avec hydrogel et methode de correction pour aberrations d'ordre eleve de la vue Download PDF

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Publication number
WO2004099858A1
WO2004099858A1 PCT/US2003/027478 US0327478W WO2004099858A1 WO 2004099858 A1 WO2004099858 A1 WO 2004099858A1 US 0327478 W US0327478 W US 0327478W WO 2004099858 A1 WO2004099858 A1 WO 2004099858A1
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WIPO (PCT)
Prior art keywords
contact lens
lens
center
trial
subject
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PCT/US2003/027478
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English (en)
Inventor
Stephen A. Dunn
Charles E. Campbell
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Polyvue Technologies, Inc.
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Application filed by Polyvue Technologies, Inc. filed Critical Polyvue Technologies, Inc.
Priority to AU2003268377A priority Critical patent/AU2003268377A1/en
Publication of WO2004099858A1 publication Critical patent/WO2004099858A1/fr

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Classifications

    • G—PHYSICS
    • G02—OPTICS
    • G02C—SPECTACLES; SUNGLASSES OR GOGGLES INSOFAR AS THEY HAVE THE SAME FEATURES AS SPECTACLES; CONTACT LENSES
    • G02C7/00—Optical parts
    • G02C7/02—Lenses; Lens systems ; Methods of designing lenses
    • G02C7/04—Contact lenses for the eyes
    • G02C7/048—Means for stabilising the orientation of lenses in the eye
    • G—PHYSICS
    • G02—OPTICS
    • G02C—SPECTACLES; SUNGLASSES OR GOGGLES INSOFAR AS THEY HAVE THE SAME FEATURES AS SPECTACLES; CONTACT LENSES
    • G02C7/00—Optical parts
    • G02C7/02—Lenses; Lens systems ; Methods of designing lenses
    • G02C7/021—Lenses; Lens systems ; Methods of designing lenses with pattern for identification or with cosmetic or therapeutic effects
    • G—PHYSICS
    • G02—OPTICS
    • G02C—SPECTACLES; SUNGLASSES OR GOGGLES INSOFAR AS THEY HAVE THE SAME FEATURES AS SPECTACLES; CONTACT LENSES
    • G02C7/00—Optical parts
    • G02C7/02—Lenses; Lens systems ; Methods of designing lenses
    • G02C7/04—Contact lenses for the eyes
    • G—PHYSICS
    • G02—OPTICS
    • G02C—SPECTACLES; SUNGLASSES OR GOGGLES INSOFAR AS THEY HAVE THE SAME FEATURES AS SPECTACLES; CONTACT LENSES
    • G02C2202/00—Generic optical aspects applicable to one or more of the subgroups of G02C7/00
    • G02C2202/04—Lenses comprising decentered structures
    • G—PHYSICS
    • G02—OPTICS
    • G02C—SPECTACLES; SUNGLASSES OR GOGGLES INSOFAR AS THEY HAVE THE SAME FEATURES AS SPECTACLES; CONTACT LENSES
    • G02C2202/00—Generic optical aspects applicable to one or more of the subgroups of G02C7/00
    • G02C2202/22—Correction of higher order and chromatic aberrations, wave front measurement and calculation

Definitions

  • the present invention relates to contact lenses, particularly hydrogel contact lenses, and to correction of higher order optical aberrations of the eye.
  • U.S. Patent No. 5, 1 14,628 describes a method for manufacturing contact lenses, especially individually fitted contact lenses.
  • the topography of the eye is measured three-dimensionally, the geometry of the rear face of the lens is determined so as to fit the topography measured, the optical effect of a lachrymal lens which is formed between the rear face of the lens and the surface of the eye is determined, the geometry of the front face of the lens is determined taking into account the optical effect of the lachrymal lens and the sight correction to be achieved, and the data so obtained for the lens geometry of the front and rear faces of the lens are stored and transferred to a control arrangement for the manufacture of the lens in a machine tool.
  • U.S. Patent No. 6,086,204 describes methods and devices that are needed to design and fabricate modified surfaces on contact lenses or on corneal tissue that correct the eye's optical aberrations beyond defocus and astigmatism.
  • the patent discusses means for: 1) measuring the eye's optical aberrations either with or without a contact lens in place on the cornea, 2) performing a mathematical analysis on the eye's optical aberrations in order to design a modified surface shape for the original contact lens or cornea that will correct the optical aberrations, 3) fabricating the aberration-correcting surface on a contact lens by diamond point turning, three dimensional contour cutting, laser ablation, thermal molding, photolithography, thin film deposition, or surface chemistry alteration, and 4) fabricating the aberration-correcting surface on a cornea by laser ablation.
  • U.S. Patent 6,086,204 are accomplished by mathematical methods which analyze the wavefront slope data as well as the shape of the subject's original contact lens or corneal surface in order to design a modified surface shape for the original contact lens or cornea that corrects the aberrations.
  • original optical surface in U.S. Patent 6,086,204 is meant the anterior surface of either a contact lens placed on the cornea or, in the absence of a contact lens, the cornea itself.
  • the steps in that mathematical method are: 1) determining the normal vectors to the original contact lens or corneal surface, 2) from these normal vectors and the wavefront slope data, determine the partial derivatives of the surface for the modified contact lens or corneal surface that corrects the aberrations, and 3) fitting these partial derivatives of the aberration- correcting surface with the corresponding partial derivatives of a polynomial expression that best represents the aberration- correcting surface. From those methods, a mathematical expression for the aberration-correcting is obtained.
  • fabrication devices and methods are provided to fabricate the modified aberration-correcting surfaces designed by the mathematical methods described.
  • fabrication devices and methods mentioned include those of diamond point micro-machining, laser ablation, thermal molding, photolithography and etching, thin film deposition, and surface chemistry alteration.
  • fabrication devices and methods mentioned are those associated with laser ablation as used with photorefractive keratectomy (PRK) and laser in-situ keratomileusis (LASIK).
  • the subject is examined and data gathered for correcting optical aberration as follows.
  • the examiner accurately positions the subject's eye so that the entering beam is accurately centered with respect to the subject's pupil.
  • the positioning of the subject's eye with respect to the instrument beam is controlled by a mechanism consisting of an x-y-z translation stage that moves a chin and head rest used by the subject.
  • the subject is asked to look through an eyepiece at the point of light formed within the field stop, while the examiner adjusts the location of subject's eye so that the beam passes through the center of the pupil.
  • the examiner Prior to taking a measurement, the examiner focuses the eyepiece trying to achieve the brightest and best-focused image of the array of focal spots seen on the computer monitor.
  • the operator presses a key which commands the computer to acquire an image of the array of spots.
  • a key which commands the computer to acquire an image of the array of spots.
  • as many as ten successive images may be acquired for subsequent averaging to improve the signal/noise ratio of the data.
  • the image analysis program carries out the following steps: 1) subtracts ""background” light from the image, 2) determines the x & y coordinates (in pixels) of the centroid for each of the focal spots, 3) subtracts the x & y pixel coordinate values from a corresponding set of reference values (obtained from a calibration with a diffraction-limited reference lens), 4) multiplies the difference values (in pixel units) by a calibration factor which gives for each location in the pupil the components in the x and y directions of the wavefront slope error measured in radians.
  • the components of the wavefront slope error, labeled Bx and By, are the essential measurement data of the wavefront sensor.
  • U.S. Patent 6,305,802 Bl describes a system and method for correcting optical aberration that integrates corneal topographic data and ocular wavefront data with primary ametropia measurements to create a soft contact lens design.
  • Corneal topographic data is used to design a better fitting soft contact lens by achieving a contact lens back surface which is uniquely matched to a particular corneal topography, or which is an averaged shape based on the particular corneal topography.
  • the unique back surface design also corrects for the primary and higher order optical aberrations of the cornea.
  • ocular wavefront analysis is used to determine the total optical aberration present in the eye. The total optical aberration, less any corneal optical aberration corrected utilizing the contact lens back surface, is corrected via the contact lens front surface design.
  • the contact lens front surface is further designed to take into account the conventional refractive prescription elements required for a particular eye.
  • Suitable wavefront correction of vision can enhance acuity and also can enhance vision under low-light conditions such as nighttime driving.
  • Candidates for wavefront correction include those seeking "super vision” or enhanced nighttime vision, as well as people with keratoconus, irregular astigmatism, corneal scarring, or surgically induced irregularity, who are difficult or impossible to have their vision fully corrected by conventional means. People with such difficult vision correction problems can be as much as 38% of the population. These people would experience limited improvements to their vision with today's spherocylindrical correction, whether contact lens or refractive surgery, that only addresses the lower three of the more than 18 orders of Zernike terms that express various orders of optical aberrations.
  • RK Random Keratotomy
  • PRK Photorefractive Keratectomy
  • the present invention recognizes that, with each step of improvement in the correction of vision, there has come the need to better control placement of the correction with respect to the eye.
  • the vision correction was essentially the same even though the lenses were decentered with respect to the pupil of the eye or if the lenses were rotated. Only the distance the lenses were held from the eye was really important. This is because lenses to correct simple defocus are rotationally symmetric.
  • correction for astigmatism was added to that for defocus, freedom to rotate the lenses to an arbitrary orientation was lost although the correction was still quite insensitive to decentering. This is because lenses to correct astigmatism, although not rotationally symmetric, still retain a translational symmetry.
  • higher order corrections are added, all symmetry is lost and the correction must be well aligned with the pupil of the eye both with respect to centering, rotation and eye movement, thus, eliminating spectacles as an option.
  • a trial contact lens has a front surface, a back surface and a center.
  • the front or back surface bears indicia for determining the precise location and orientation of the trial contact lens when positioned on a cornea of a subject.
  • the indicia comprise (i) a first marking indicative of the center of the trial contact lens and (ii) a second marking identifying a predetermined bottom of the trial contact lens and an angular orientation (i.e., displacement) of the contact lens from a vertical axis through the center of the cornea when the trial contact lens is positioned on the cornea of the subject.
  • the front surface of the trial contact lens has further comprises a slaboff surface positioned at the predetermined bottom of the lens.
  • the first marking comprises a ring having a diameter at least as large as the pupil of the subject, the ring being centered on the center of the contact lens.
  • the second marking comprises (i) an arrow shaped line located on a center axis of the lens and pointing in a direction of the predetermined bottom of the lens and (ii) two line markings located on a line through the center of the lens and perpendicular to said centerline, the two line markings being located on opposite sides of the center of the lens, thereby indicating a horizontal line when the center axis is vertical.
  • the first marking comprises a ring having a diameter at least as large as the pupil of the subject, the ring being centered on the center of the contact lens
  • the second marking comprises (i) an arrow shaped fine located on a center axis of the lens and pointing in a direction of the predetermined bottom of the lens and (ii) two line markings located on a line through the center of the lens and perpendicular to said centerline, the markings being located on opposite sides of the center of the lens, thereby indicating a horizontal line when the center axis is vertical.
  • the set of markings extend outward from a perimeter of the ring.
  • the present invention also provides a method for correcting total optical aberration including higher order optical aberration in an eye of a subject, the method comprising: measuring data indicative of the wavefront error of the eye of the subject; providing a trial contact lens as described above; determining the precise location of the trial contact lens relative to the pupil of the subject, including the offset distance between the center of the trial contact lens and the center of the pupil and/ or the angular displacement of the trial contact lens with a vertical axis through the pupil of the subject with head positioned normally when the trial contact lens is worn by the subject; manufacturing a contact lens that is structured and arranged to locate on the eye of the subject in the same position and orientation as the trial contact lens; and providing the contact lens with optical aberration correction for the subject by using the measured data, the offset distance between the center of the trial contact lens and the center of the pupil and/or the angular displacement of the trial contact lens with a vertical axis through the pupil of the subject with head positioned normally when the trial contact lens is worn by the subject so that the optical aberration correction is applied
  • the process of creating a hydrogel contact lens that will correct the optical errors of the eye beyond the common sphero cylindrical errors begins with the measurement of the errors of the eye using advanced refraction systems, often referred to "wavefront refractors".
  • advanced refraction systems often referred to "wavefront refractors".
  • Wavefront refractors One example of such a refracting system is sold by Topcon Medical Systems, Inc., Paramus, New jersey.
  • Such devices are advanced automatic refractors that measure with higher data density than the usual automatic refractors and so can measure more complex errors than can the simpler refractors.
  • the refraction information is usually presented in the form of a set of numbers known as Zernike coefficients.
  • Zernike coefficients are a set of weighting values used with standardized Zernike polynomial functions.
  • the sum of the weighted Zernike polynomial functions represents the wavefront error, expressed as an optical thickness, that must be removed to fully correct the vision of the eye. It may be thought of as an "error lens" which, if removed, removes the aberrations of the eye.
  • This data for this correction or "error lens” is expressed with respect to the visual axis or the pupil center. Information also is needed to tell where the visual axis or the pupil center lies within the hydrogel contact lens so that the correction may be correctly placed on that contact lens.
  • a trial contact lens having the same shape as the final vision-corrected contact lens, but with orientation marks on it, is used for fitting the patient and taking measurements for manufacturing the vision- corrected contact lens. This trial contact lens is placed on the eye and allowed to stabilize with respect to the eye. Then a photograph is taken of the eye/lens combination allowing the pupil of the eye and the alignment marks on the lens to be seen simultaneously.
  • the lens has taken its customary position so, by noting the angle between the orientation marks and local horizontal (accomplished by insuring the camera is held level and the person has taken a natural eye and head position), a rotation correction angle is made available. Centering marks on the lens allow the position of the pupil center with respect to the lens to be assessed.
  • the design of the contact lens should preferably be such that little if any change in centering occurs during wear and that the lens does not rotate during wear. If this is not the case, the correction will not be optimal. Thus, it also is preferable that the trial contact lens and final vision-corrected contact lens have the same centering and rotational stability characteristics.
  • the lens can be made.
  • the lenses may be made in any conventional way.
  • a single point diamond tool lathe with ability to turn complex shapes can be used to create the front surface of the lens on a dehydrated lens.
  • One example of such a lathe is manufactured by DAC International of Carpenteria, CA.
  • the lens can be created by turning the front surface using the special lathe on a standard dehydrated contact lens button and then turning a conventional back surface to the lens to create a finished lens.
  • the lens also can be created by turning the front surface on a semifinished cast molded lens whose back surface is created in a finished geometry in the molding process and remains attached to the back surface mold during process of turning the front surface. The lens is subsequently hydrated to create a finished hydrogel lens.
  • a hydrogel contact lens blank with the proper characteristics is affixed to a hold fixture and the front surface of the lens is shaped using an excimer laser system of the same type used to ablate the human cornea during a surgical refractive correction procedure.
  • a semi- finished cast molded lens in the dehydrated state, attached to the back surface mold and with a finished front surface has its front surface shaped by an excimer laser system. The lens is then detached from the mold and hydrated.
  • a master for the aberration corrected lens is made using, for example, a single point diamond tool lathe, or the like.
  • the master is then used to make a mold for cast molding the hydrogel lens. This method permits the subject to use disposable contact lenses.
  • FIG. 1 is a cross- sectional view of a hydrogel contact lens.
  • FIG. 2 is a plan view of the hydrogel contact lens showing alignment markings in accord with the present invention.
  • both the trial contact lens and the finished vision-corrected contact lens must be designed and made to provide the same orientation.
  • the trial contact lens and the finished vision-corrected contact lens are provided with a like set of orientation markings.
  • a preferred design to maintain orientation provides a lens wherein the optical center of the front surface in the optical zone is displaced about 0.15 mm along the vertical axis from the optical center of the back surface and, in addition, a "slaboff' region preferably is created on the inferior edge of the lens.
  • other displacements can be suitable.
  • the lens orientation can be stabilized using a prism ballast.
  • a contact lens 1 (shown in vertical cross section) has the back surface center of curvature 3, which is located on back surface optical axis 6, is 0.15 mm above the front surface center of curvature 4, which is located on the optical axis of the front surface 7.
  • the front surface 2 of the lens continues from the top of the lens until it joins the "slaboff surface 5, the center of curvature 8 of which is located on back surface optical axis 6.
  • This hydrogel contact lens cross section design causes the lens to orient itself on the eye via the action of the lids during the natural blink process so that the "slaboff is essentially located inferiorly, provided that the lens is sufficiently thin and flexible.
  • a preferred orientation marking is illustrated in FIG. 2.
  • a colored ring 10 is printed on the contact lens 9.
  • the ring is a blue ring, 10 mm in diameter, and is centered with outer edge of the lens, the diameter of which is 14.5 mm.
  • Two printed alignment marks 11, 12 are located on the horizontal axis and are attached to the ring.
  • Another alignment mark in the form of an arrow 13 is printed (joined to the ring) at 90 degrees from the horizontal marks and is located in the area of the "slaboff and to indicate the bottom of the lens.
  • the boundary between the optical zone of the lens and the "slaboff area is indicated by curved line 14.
  • the ring and alignment marks can be provided by any means capable of providing a mark that is visible under predetermined conditions, including etching, engraving, and molding into the lens.
  • Printing can use indicators that are visible only under a predetermined frequency of irradiation.
  • the arrow can be part of the right horizontal alignment mark instead of a separate mark. Rotation of the trial lens is measured then from the zero axis position instead of from the vertical axis when using the separate arrow 13.
  • the information necessary to shape the front surface of the hydrogel contact to give full optical correction of the eye consists of (i) characterization of the wavefront error of the eye, typically given as a set of Zernike polynomial function coefficients along with the pupil diameter used to create these coefficients, (ii) the index of refraction of the hydrated contact lens material, (iii) the offset of the pupil center (or the visual axis) from the center (or the visual axis)of the hydrogel contact lens when it is worn by the patient and (iv) the rotation of the lens from horizontal (or vertical) when worn.
  • the Zernike coefficients are then used to calculate the wavefront error over the surface of the pupil in terms of optical path length.
  • optical path lengths are then converted to effective path length in lens material by multiplying the optical path length values by the quantity (the index of refraction of hydrated lens material equals 1).
  • the path lengths at each location on the lens front surface of the lens (which is located over the pupil of the eye when the vision-corrected contact lens is positioned on the eye) provides the amount of hydrated lens material that should be removed from the lens blank to make the vision-corrected contact lens.
  • the procedure also can use (perhaps, preferably) a lens blank having a predetermined spherical, spherical plus cylindrical (i.e., spherical plus astigmatic), or spherical equivalent optical power, the particular lens blank being selected based on the optical correction required by the specific patient.
  • a lens blank having a predetermined spherical, spherical plus cylindrical (i.e., spherical plus astigmatic), or spherical equivalent optical power, the particular lens blank being selected based on the optical correction required by the specific patient.
  • the contact lens fitter i.e., for example, ophthalmologist or optometrist
  • the contact lens fitter can have a set of trial contact lenses having various optical corrections, for example, from plus 15 diopters to minus 15 diopters in 0.25 diopter increments.
  • the fitter selects the trial lens having base optical correction closest to the optical correction needed for the patient and obtains the wavefront error of the eye with that trial lens.
  • the final vision-corrected lens is made having both the base optical correction and correction for wavefront error of the eye.
  • a zero power lens is found to have a front surface curvature of 8.31 mm.
  • a trial contact lens having a base optical corrective power also can be readily designed by those skilled in the art.
  • the semi-finished lens preferably is designed to have basic optical correction, i.e., a selected spherical, spherical plus cylindrical, or spherical plus astigmatic, or spherical equivalent optical correction (or can be a zero power lens) when hydrated. It is preferred that the semi-finished lens have an optical correction as close as possible to the basic corrective power need by the patient and that the initial front surface preferably is of optical quality. This quality is preferred because the laser only removes the material necessary to create the correction and any roughness or optical imperfection in the initial lens surface is not corrected merely by the procedure for correcting the higher order aberrations.
  • basic optical correction i.e., a selected spherical, spherical plus cylindrical, or spherical plus astigmatic, or spherical equivalent optical correction (or can be a zero power lens) when hydrated. It is preferred that the semi-finished lens have an optical correction as close as possible to the basic corrective power need by the patient and that the initial
  • the front surface need not have as high optical quality because the lathe controls the total final geometry.
  • Instruction to the lathe must include, not only the amount of material to be removed to provide the correction but also, the information on the underlying lens blank surface geometry that was used as the trial lens, because the lathe must also create this underlying shape.
  • the surface instructions for the underlying surface and the overlying correction are combined into one set of lathe instructions.
  • a patient in need of vision correction is examined by a trained professional, typically an ophthalmologist or optometrist.
  • the patient is fitted with a trial lens, preferably a lens that has required spherical optical power to correct the patient's vision.
  • an eye refractor is used to determine optical aberration.
  • the information received from the measuring refractor instrument will consist of a set of numbers.
  • the radius of the pupil of the eye is used to generate a set of numbers known as the Zernike coefficients.
  • the further set of four numbers consists of the horizontal and vertical displacements of the center of the pupil from the geometric center of the trial lens, the rotation of the trial lens from local horizontal and the power of the trial lens, given in diopters.
  • the numbers are used in the following way.
  • the set of Zernike coefficients, along with the value of the radius of the pupil used to generate them, are used to reconstruct a surface. That surface is the wavefront error measured by the instrument. This is done by choosing a polar coordinate system grid, one that is sized for the lathe system to be used, and calculating the height of the surface at each point in the grid as follows.
  • the Zernike functions can be written as a product of a radial polynomial
  • R' n m ' a meridional function
  • MTM a meridional function
  • NTM a normalization function
  • M (n, m) sin (m ⁇ ) if m ⁇ 0
  • the values S(r, ⁇ ) represent the change in optical path length needed at
  • n is the index of refraction of a material and that material forms an interface with air whose index of refraction is 1.0
  • the change in the optical path length of light passing through the material when a thickness of the material x is removed from the surface is (n- l)x. Therefore, if one desires to remove an optical path-length S(r, ⁇ ), the amount of material to remove, T(r, ⁇ )
  • n S(r, ⁇ )/(n-l). The value of n to choose for a hydrated Optifilcon-A® lens
  • the lathe cuts a de-hydrated lens that will swell as it hydrates so one need not cut as much material as found above. Indeed, the amount of material to remove at a location (r, ⁇ ) is the value found above divided by the material
  • the preferred way to deal with this decentration and rotation problem is to use a method in which the Zernike coefficients are transformed so that they represent the surface in a new coordinate system that is decentered and rotated from the original. Once determined, it is these coefficients, not that ones sent from the measuring refraction device, that are used in Equation (5).
  • Modifying an un-hydrated lens with a lathe is a sculpture process and so material can only be removed, not added. However the thickness values given by T(r, ⁇ ) can taken both positive and negative values so to insure that all values
  • the corrective surface modified so that all values are equal to or less than zero goes out to a certain diameter and then stops. But in the actual lens this surface must blend smoothly into the predicate lens surface.
  • a transition zone is created between the edge of the correction zone and the unaltered predicate front surface.
  • the preferred way is to extend the correction surface out to the edge of the chosen transition zone with a smooth continuation of the correction surface by using the method of resizing the coefficients. This is done with an analytical technique that creates a set of coefficients from an original set appropriate for an enlarged pupil diameter.
  • This method guarantees that the area with in the original surface is not changed when the surface is reconstructed with the new coefficient set and guarantees that the added surface area joins smoothly to the original area.
  • This resizing step is actually done before the translation and rotation step discussed above is done and it is the resized coefficients that are translated and rotated.
  • a transition mask is created with the following characteristics.
  • the mask is created with the same location values as are used to generate the translated and rotated surface. At each location with in the correction area, the mask is given a value 1.0.
  • the mask takes values that decrease smoothly in radial directions from the center of the correction area and become 0 at and beyond the edge of the transition area.
  • This mask an array of value with one-to one correspondence with the expanded correction area, also an array of values, it multiplied on a point-by-point basis with the expanded correction array. The total effect is to cause no change in the correction area and to smoothly blend the surface to zero (no change) at the edge of the transition area.
  • the final step is to generate a point file for the front surface of the predicate lens, using the known value for the trial lens power used, and add to t the blended correction area points file. The result is the surface that the lathe must cut.
  • This information is provided to the lathe and a lens is made.
  • the lens is provided to the patient and provides total vision correction to the patient.
  • the information determined by the eye refractor can be used to make a mold for forming the contact lens, instead of making the lens directly.
  • the term "slaboff" region means a region of the contact lens having a discontinuous change in thickness as a result of a change in the radius of the surface, the result causing the lens to be stably oriented by the normal blinking of the eye.

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  • Health & Medical Sciences (AREA)
  • Ophthalmology & Optometry (AREA)
  • Physics & Mathematics (AREA)
  • General Health & Medical Sciences (AREA)
  • General Physics & Mathematics (AREA)
  • Optics & Photonics (AREA)
  • Eyeglasses (AREA)

Abstract

Cette invention concerne une méthode permettant de corriger une aberration optique totale, y compris une aberration de la vue d'ordre élevé. On mesure des données renseignant sur l'erreur de front d'ondes de l'oeil du sujet. On utilise une lentille de contact d'essai présentant une surface avant, une surface arrière et un centre, l'une au moins des surfaces avant ou arrière portant des repères permettant de déterminer précisément la positon et l'orientation de ladite lentille de contact sur la cornée. On trouve un premier repère correspondant au centre de la lentille de contact d'essai et un second repère permettant de déterminer un fond de ladite lentille de contact et une orientation angulaire à partir de l'axe vertical passant par le centre de la cornée lorsque cette lentille est positionnée sur la cornée du sujet. L'emplacement précis de la lentille de contact d'essai est déterminé par rapport à l'axe de vision du sujet, y compris la distance de déport entre le centre de la lentille de contact d'essai et le centre de la pupille, ainsi que la distance angulaire de ladite lentille à l'axe vertical traversant la pupille lorsque la tête du sujet se trouve en position normale. On fabrique une ébauche de lentille de contact qui est placée sur l'oeil du sujet dans la même position et selon la même orientation que la lentille de contact d'essai. Cette ébauche prend en compte la correction d'aberration optique fournie par les donnée mesurées, la distance de déport entre le centre de la lentille de contact d'essai et le centre de la pupille, et le rapport entre le fond de la lentille de contact d'essai et le fond de la pupille par rapport à un sol horizontal de telle sorte que la correction d'aberration optique soit appliquée précisément à l'ébauche de lentille de contact et que la correction d'aberration soit positionnée correctement sur la pupille et permette d'obtenir une lentille de contact à vision corrigée.
PCT/US2003/027478 2002-08-30 2003-09-02 Lentille de contact avec hydrogel et methode de correction pour aberrations d'ordre eleve de la vue WO2004099858A1 (fr)

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US60/407,316 2002-08-30

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Cited By (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
EP2287656A1 (fr) * 2009-08-17 2011-02-23 Hecht Contactlinsen GmbH Procédé de fabrication de lentilles de contact adaptées aux yeux d'une personne
WO2013110059A1 (fr) * 2012-01-20 2013-07-25 University Of Rochester Système et procédé de conception de lentilles ophtalmiques guidées par front d'onde
EP2778760A1 (fr) * 2013-03-15 2014-09-17 Johnson & Johnson Vision Care, Inc. Dispositifs ophtalmiques avec caractéristiques de stabilisation
WO2015080938A1 (fr) * 2013-11-26 2015-06-04 Johnson & Johnson Vision Care, Inc. Détermination d'alignement de lentille sur un œil au moyen de mesures de front d'onde optique
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US9547182B2 (en) 2009-02-02 2017-01-17 Johnson & Johnson Vision Care, Inc. Of myopia control ophthalmic lenses
EP2287656A1 (fr) * 2009-08-17 2011-02-23 Hecht Contactlinsen GmbH Procédé de fabrication de lentilles de contact adaptées aux yeux d'une personne
WO2013110059A1 (fr) * 2012-01-20 2013-07-25 University Of Rochester Système et procédé de conception de lentilles ophtalmiques guidées par front d'onde
US9925038B2 (en) 2012-01-20 2018-03-27 University Of Rochester System and method for designing wavefront-guided ophthalmic lenses
EP2778760A1 (fr) * 2013-03-15 2014-09-17 Johnson & Johnson Vision Care, Inc. Dispositifs ophtalmiques avec caractéristiques de stabilisation
US9164297B2 (en) 2013-03-15 2015-10-20 Johnson & Johnson Vision Care, Inc. Ophthalmic devices with stabilization features
US9810922B2 (en) 2013-03-15 2017-11-07 Johnson & Johnson Vision Care, Inc. Ophthalmic devices with stabilization features
WO2015080938A1 (fr) * 2013-11-26 2015-06-04 Johnson & Johnson Vision Care, Inc. Détermination d'alignement de lentille sur un œil au moyen de mesures de front d'onde optique
JP2017500604A (ja) * 2013-11-26 2017-01-05 ジョンソン・アンド・ジョンソン・ビジョン・ケア・インコーポレイテッドＪｏｈｎｓｏｎ ＆ Ｊｏｈｎｓｏｎ Ｖｉｓｉｏｎ Ｃａｒｅ， Ｉｎｃ． 光学波面測定値を用いた眼上におけるレンズ調心の決定
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RU2667314C1 (ru) * 2013-11-26 2018-09-18 Джонсон Энд Джонсон Вижн Кэа, Инк. Определение центрирования линзы на глазу по измерениям оптического волнового фронта
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