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
  • G02C7/024—Methods of designing ophthalmic lenses
  • G02C7/028—Special mathematical design techniques
• • 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 or corneal implants; 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
  • 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 or corneal implants; 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
  • A61F2/1637—Correcting aberrations caused by inhomogeneities; correcting intrinsic aberrations, e.g. of the cornea, of the surface of the natural lens, aspheric, cylindrical, toric lenses
• • 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
  • G02C7/041—Contact lenses for the eyes bifocal; multifocal
  • G02C7/042—Simultaneous type
• • 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
  • G02C7/06—Lenses; Lens systems ; Methods of designing lenses bifocal; multifocal ; progressive
• • 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
• • 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
  • G02C2202/20—Diffractive and Fresnel lenses or lens portions
• • 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

• OPHTHALMIC LENS OPHTHALMIC LENS OBTAINED ACCORDING TO
• the present invention relates to a method for determining the configuration of an ophthalmic lens. It also relates to an ophthalmic lens obtained according to this method and to a method for manufacturing such an ophthalmic lens.
• the present invention deals with ophthalmic lenses with extended depth of focus (PDF) and therefore with corresponding extended field depths (PDCs).
• PDF extended depth of focus
• PDCs extended field depths
• These refractive-diffractive hybrid lenses use on one surface a diffractive mask and on the other an aspherical surface. These lenses allow to choose the depth of focus, even very wide, while maintaining an acceptable resolution on the field of focus.
• the surface bearing the diffractive mask can be replaced by an aspherical surface with close optical characteristics.
• the hybrid lens is then composed of two aspherical surfaces.
• the depth of focus can be created on segments for example for near vision and / or for distant vision. Near vision usually has a depth of focus and thus a lower depth of field than distant vision. It is therefore possible by increasing the depth of focus for near vision only to obtain a significant total depth of focus.
• the method of the invention is applicable to all ophthalmic lenses such as:
• SA spherical aberrations
• a "perfect" lens without aberrations, makes it possible to define a specific plane of the object space which is precisely the conjugate of the receiving plane (film, camera, retina, sensor, etc.) in the image plane.
• This is, in the object plane, the focus plane object.
• the depth of focus PDF is by definition the distance on the axis of the lens on the image side where the dimension of the image, called circle of least confusion (CMC) if the object is punctual, becomes confused, that is, to say where the observer recognizes a loss of resolution.
• CMC circle of least confusion
• the defocus becomes clearly perceptible.
• the depth of field PDC is the corresponding distance from the object point, from the object side, before the image reaches the maximum tolerable dimension of the circle of least confusion.
• modulation transfer function or modulation transfer function (MTF).
• MTF modulation transfer function
• MTF modulation transfer function
• Many 1OL intraocular lenses are produced today with a correction that can be complete, partial or no spherical aberrations SA of the cornea of the user.
• a partial correction allows to obtain an increase of the depth of focus. Although users seem satisfied with this increase in depth of focus, this increase remains modest, typically a few tenths of a millimeter. It is obtained essentially at the expense of the resolution and the modulation transfer function.
• Intraocular lenses with a partial correction of spherical aberrations of the cornea, as well as those that have no correction, have the advantage of being less sensitive to decentration, tilt and a change of position when they are implanted in the eye of a patient.
• lenses in which spherical aberrations of the cornea are completely corrected by the choice of a suitable aspherical surface have better resolution.
• they have a depth of focus and therefore a shallower depth of field. They are also sensitive to decentering, tilt and change of position.
• Technis Multifocal ZM 9000 (Advanced Medical Optics, Inc.). It is a diffractive silicone intraocular lens with an aspherical surface. This lens was the first intraocular lens with commercially available aspherical surface that compensates for monochromatic spherical aberrations of the cornea. It has a negative spherical aberration correction to compensate for positive spherical aberration of the cornea. The compensation is calculated for SA aberration values measured on a population sample and does not target a custom correction. The performances of these lenses are particularly sensitive to tilt and decentration of the implant. In this case, the eye - lens visual system will have a very good resolution and a depth of focus and therefore a much lower field of view than in the case where the correction of spherical aberrations of the system is partial or nil.
• Akreos Adapt Advanced Optics (Bausch & Lomb, Inc.) is an asymmetric, biconvex lens with aspheric anterior and posterior surfaces that eliminate spherical aberration SA from the lens.
• the pseudophakic eye retains a positive value of monochromatic spherical aberration due to the cornea, which gives it an improved depth of focus and creates a certain pseudo-accommodation.
• this lens has a constant power over its entire surface which allows it to be more tolerant to misalignment and tilt than a lens with correction of negative spherical aberrations SA to compensate for the aberration SA of the cornea of the user.
• uncertainties exist in the manufacture of a lens and the choice of lens to implant in the eye of a patient.
• manufacturers do not always accurately measure the power (or focal length) of the lens and provide approximate values.
• the uncertainties may be greater because more complex surfaces are treated.
• tilt, rotation, centering, sagging, and other positioning errors in the eye may increase the degradation of visual acuity. These errors also depend on the construction of the lens.
• the intraocular lenses should be tailored to the specific needs of the patient.
• Typical values are, for example, + 0.27 ⁇ m for spherical aberration SA of the normal cornea of a young eye. This value can be compensated for by a practically equal value of negative spherical lens aberration (-0.27 ⁇ m). With age, the values of spherical SA aberration of the lens often become positive. For a sexagenarian, a typical value of the whole eye is + 0.54 ⁇ m. Obviously, ocular characteristics vary from one individual to another, as do the values of aberrations.
• the present invention proposes to overcome the disadvantages of ophthalmic lenses of the prior art by providing lenses having a PDC depth of field and therefore also a depth of focus PDF extended compared to existing lenses.
• the extension of this depth of focus is not performed at the expense of the resolution or the FTM modulation transfer function as in the lenses of the prior art.
• the resolution / modulation transfer function FTM on the one hand and the depth of focus PDF / depth of field PDC on the other hand are relatively independent of each other, especially after implantation when the lens is combined with the eye. This independence is not complete, but allows better control of these parameters independently of one another in comparison with a conventional lens.
• one of the objectives sought by the present invention is therefore to separate, to a certain extent, the determination of the depth of field or focus of that of the resolution or of the modulation transfer function.
• the present invention further proposes to keep the resolution or the MTF modulation transfer function approximately constant on each depth-of-field segment.
• a method for determining the configuration of an ophthalmic lens for correcting the visual acuity of a user comprising the following steps: determining the shape of a corrective element Basic optics based on at least one of the following parameters:
• SA spherical aberrations
• SA spherical aberrations
• HOA higher order aberrations
• DPE diffractive phase distribution structure
• PDF desired depth of focus
• an ophthalmic lens intended to correct the visual acuity of a user, characterized in that it comprises a basic optical correction element to which is juxtaposed a diffractive phase distribution structure.
• the objects of the invention are further achieved by a method of manufacturing an ophthalmic lens whose configuration is determined according to the method of determining the configuration of a lens.
• DPE diffractive phase element
• the diffractive structure or diffractive mask can be replaced by an aspherical surface producing a similar phase distribution. It is therefore possible to use instead of the diffractive DPE phase distribution structure, a refractive surface which produces a phase distribution adapted to the creation of an extended depth of focus.
• This extension of the PDF focusing depth will generally be performed with an approximately constant FTM modulation transfer resolution / function on the window in question.
• the resolution variation on the depth of focus may be about a factor of two or three, but not an order of magnitude.
• the increase of the depth of focus can also be obtained by increasing the correction of longitudinal spherical SA aberrations.
• This correction can be positive or negative. If it is positive, it will be added to the positive spherical aberration of the cornea.
• Diffractive DPE phase distribution structures create a particular wavefront.
• the light beam thus created has features that are used here for ophthalmic lens applications and can be considered as a three-dimensional apodization of the image to achieve extension along the longitudinal axis without excessive loss on the axes. transverse.
• the diffractive phase distribution structure DPE can sometimes be replaced by an aspherical surface calculated either by unwrapping ("unwraping"), or from polynomials representing the phase (or equivalent distributions), or from phase distributions to obtain equivalent results.
• the lens namely the resolution or the FTM modulation transfer function on the one hand and the depth of focus PDF or PDC field on the other hand. These values may cover, among other things, aging effects, measurement tolerances, calculation errors, position errors and others that make the intervention of the specialist binding.
• the lens must provide a sufficient depth of focus in all cases, as well as an acceptable FTM modulation transfer resolution / function.
• Focusing depth PDF can be relatively small on a window for near vision and larger on a window for vision distant.
• Near vision usually has a PDF depth of focus and thus a lower PDC depth of field than distant vision. It is therefore possible to obtain a significant depth of focus PDF by increasing only the depth of focus PDF near vision.
• a lens according to the invention makes it possible to obtain a light tube which largely avoids parasitic images, halos and "glares".
• an ophthalmic lens including a first surface, anterior or posterior, for neutralizing or extending the aberrations (spherical, chromatic and higher orders) of the eye-lens vision system.
• This surface is in general, aspheric. It includes a second surface, posterior or anterior, formed of one or more areas that can be realized as diffractive structures or DPE ("Diffractive Phase Element") phase distribution structures.
• DPE diffractive Phase Element
• These diffractive structures can be identified, calculated, juxtaposed and then manufactured as aspherical surfaces.
• These diffractive or aspherical structures produce focal depths of PDF, thus of PDC field, variable and controllable.
• the central thickness of the lens will be chosen according to the needs: low to obtain a reduced incision of the cornea; larger if a thicker lens is sought to better fill the capsular bag. PDF depth of focus and resolution characteristics are obtained in large ranges of variations of this thickness.
• FIG. 1 is a sectional view of an example of an ophthalmic lens used in the present invention
• the concave refractive surface is aspherical and the other surface which bears the diffractive phase distribution structure is flat;
• FIG. 2 is a schematic sectional view of an ophthalmic lens according to the present invention. other forms of surfaces are possible;
• FIG. 3 schematically shows the paths of different rays through a lens; the circle of least confusion CMC, the paraxial focusing plane and the marginal focusing plane are represented;
• FIG. 4 illustrates the PDC depth of field of a lens
• FIG. 5 illustrates the segmentation and depth of focus according to this invention
• FIG. 6a represents an example of the depth of field obtained with a mono-focal ophthalmic lens of the prior art
• FIG. 6b represents an example of the depth of field obtained with an ophthalmic lens according to the invention.
• FIG. 7 represents an example of the focusing depth of a diffractive structure as used in the present invention.
• the abscissae are in m and the intensities in ordinates are arbitrary;
• Fig. 8 is an example of the image-side intensity distribution obtained with a lens according to the present invention.
• the abscissae are in m and the ordinate intensities are arbitrary.
• the method for determining the configuration of a lens as described in the present application can be split into three steps. One of these steps comprises determining the shape of a basic optical corrector element 10 on the basis of parameters such as the desired final power for the ophthalmic lens, correcting or not aberrations of the lens or lens. the user's cornea, such as spherical aberrations, chromatic aberrations or higher-order aberrations, etc.
• This basic optical correction element may have a plane, convex, concave, toric and / or aspherical surface.
• the resulting lens may be of positive, negative or zero power; it may also be multifocal or toric particular.
• Another step includes determining the profile of a diffractive DPE phase distribution structure with the objective of increasing the depth of focus PDF or depth of field PDC.
• the third step is the juxtaposition of the diffractive phase distribution structure and the basic optical corrector element so as to obtain a hybrid ophthalmic lens 11.
• an ophthalmic lens according to the invention may have a face, for example the posterior, planar, spherical, aspherical or toric surface and may be used to partially, totally or not at all compensate for spherical aberrations or other aberrations of the user's lens or cornea.
• the second face of the lens for example the anterior face, may include a structure for increasing the depth of field PDC. It is possible to consider the posterior face as one of the faces of the basic optical correction element 10 and the anterior face as the juxtaposition of this basic optical correction element.
• the lens is also possible to invert the lens so that the posterior face has the diffractive DPE phase distribution structure. In this case, however, the lens is not simply inverted, but the determination of the structure and power must be recalculated.
• the diffractive DPE phase distribution structure essentially determines the depth of focus and will be little affected by the choice of aberration correction, in contrast to conventional conventional lenses.
• the shape of the basic optical corrector element 10 essentially determines the resolution of the lens and the visual system after implantation.
• Such a correction element is illustrated in FIG. 1. This element can be chosen, among other things, according to the following criteria: • power of the desired lens;
• Neutralization of spherical aberrations SA of the lens A lens without correction of the spherical aberration SA will make it possible, after implantation, to obtain an ocular system having a spherical aberration due to the cornea; • creation of negative spherical aberration SA for the 1OL lens.
• the value of the aberration correction SA will be chosen to fully or partially compensate for the generally positive SA aberration of the user's cornea. This aberration of the cornea can be measured on the patient or correspond to selected average values on a population group.
• the resolution of the visual system will be optimum if the spherical aberrations SA of the ocular system with the lens 1OL are zero.
• the basic optical correction element 10 will have an aspherical surface.
• the sagittal distance of such an aspheric surface will be given by the equation below:
• c is the curvature at the center of the surface
• k is the taper ce
• V (dif) is negative while V (ref) is positive.
• a hybrid lens gives:
• V (dif) is constant and negative, (see equation 2), and V (ref) is known.
• the two equations above are reduced to calculating two unknowns P (ref) and P (dif) to neutralize the chromatic aberrations.
• One of the surfaces of the lens is used to increase the depth of focus PDF / depth of field PDC.
• This surface can be considered as the juxtaposition of the diffractive DPE structure and the surface of the basic optical correction element 10.
• Figure 3 is a representation of the optical ray plots in the focal planes, respectively paraxial and marginal.
• the depth of focus PDF is the product of the diameter C of the circle of least confusion allowed (on the film, the camera, the retina, etc.) by the numerical aperture of the lens (See Figure 4).
• C is the diameter of the circle of least confusion in the object plane (conjugate of C defined in the image plane);
• D1 and D2 are the far and near distances of acceptable focus;
• A is the diameter of the lens, or rather of the entrance pupil;
• S is the distance between the plane of focus and the lens.
• C believes, for example by increasing the spherical aberrations of the lens, D1 increases and D2 decreases. This situation is interesting since spherical aberrations are almost always present in the eye-lens system, especially when the pupil grows beyond 3 mm.
• the distances are:
• C The less confusing circle C of a perfect lens, limited by diffraction, is generally considered as given by the Rayleigh criterion by which a wavefront deformation of ⁇ / 4 is acceptable. Practically, C will be determined from the pixel dimension of a camera or the resolution of the retina, the resolution of a film, and so on. To increase C, we often introduce a spherical aberration SA which can be important. This increases the depth of focus PDF and accordingly the depth of field PDC directly at the expense of the resolution.
• C is given by the resolution of the visual system.
• the corresponding depth of field is given by the formulas above.
• the distances L1 and L2 may, for example, be for L1 the reading distance and for L2 a distance away.
• the hyperfocal distance of an optical system is the distance at which the system must be focused so that the depth of field PDC extends to infinity.
• An increase in the depth of field results in a shorter hyperfocal distance so as to have a near vision image, for example adapted for reading, and a distant vision image at infinity.
• the usual intraocular lenses, after implantation have a limited depth of field created by the circle of least CMC confusion, due to the resulting spherical aberrations of the system.
• the typical values of depth of field of the usual current mono-focal lenses are of the order of 2 m to infinity. These values depend on the residual spherical aberrations of the vision system which will be different for each person, but which can be evaluated for a "standard eye".
• ⁇ is the wavelength and N is the relative aperture: focal length / effective pupil diameter.
• the typical total value of the PDF focusing depth of a single-lens 1OL lens is in the range of 0.1 to 0.2 mm.
• the aforementioned mono-focal lenses give PDF focusing depths of less than 0.2 diopters.
• a depth of focus of 0.135 mm corresponds to a distinct vision of infinity at about 2 meters, at 22 D.
• the DPE phase distribution structure can be diffractive or be transformed into an aspheric surface, as explained in detail below.
• the determination of the profile of this structure depends on the chosen depth of focus PDF. For example, it is possible to choose a depth of focus of 1 D, 2 D or more ... or equivalent values in mm representing the focal depths.
• the conversion of power into focal lengths and vice versa is well known and depends in particular on differences in refractive indices between the lens and the surrounding medium.
• Different focusing depths can be created on different areas or windows of the lens.
• the central portion of the lens may be used to create close-up focusing depth enhancing structures and the peripheral portion of the lens to create distant vision control structures or vice versa.
• the number of zones is not limited.
• the extension of the depth of focus PDF introduces a spread of intensities collected by the lens with a defined entrance pupil and reduces the energy density in the image that is formed on the retina. This may possibly cause compensation by the opening of the eye pupil and by an unconscious learning process to the low intensity image observation and may also reduce the contrast of the image.
• PNDB non-diffractive pseudo-beam
• Non-diffractive electromagnetic wave beams that propagate over long distances without changing dimensions have been defined. This type of beam has a transverse amplitude proportional to OJ ( ⁇ p), Bessel function of order 0 and the first type.
• the PNDBs are an approximation of the Bessel beams and are characterized by an almost constant intensity in an axial direction over a given region and a beam shape in the transverse direction. PNDBs have unique features such as constant axial intensity, extended propagation on the optical axis and a narrow beam. Even with approximations, these beams make it possible to obtain particular optical characteristics concerning the divergence, the depth of field and the resolution.
• the following methods related to the creation of non-diffractive Pseudo beams can be applied to the calculation of the diffractive DPE structure of the lens.
• the first step is to define the desired PDF depth of focus.
• the phase distributions of the wavefront are calculated.
• the phase distribution for a diffractive surface can be calculated from the following formula, with an even polynomial (or using the corresponding formula for an odd polynomial).
• ⁇ is the phase
• the phase distribution of the continuous wavefront is then determined by unpacking ("unwrap").
• the focusing depth PDF is represented by a "tube of light” in FIG.
• the phase distribution thus obtained is used to obtain the coefficients ⁇ of the equation (1) of a wavefront with a continuous profile.
• the number of coefficients ⁇ may be chosen, if necessary, with compromises on the profile of the wavefront. The reduction in the number of coefficients will give an approximate but sometimes satisfactory wavefront depending on the number of coefficients and the approximation introduced.
• a diffractive DPE structure can therefore be replaced by an aspherical surface.
• This area is calculated by means of a polynomial representing the phase distribution of the wavefront. This polynomial can be calculated from equation (1) giving a function of the thickness (pair if possible, but also odd or combined) for a defined wavelength. It is also possible to calculate the phase distribution from an equation directly giving the phase distribution of the wavefront, as shown below.
• phase distribution of interesting optical wave fronts are given below:
• n is the radius of the optical surface
• di are the forward and backward focal lengths.
• the phase distribution ⁇ required to create the depth of focus PDF can be obtained folded or unpacked ("wrap / unwrap") to provide a diffractive or refractive-aspheric, sometimes complex surface.
• the DPE phase distribution structures may be produced either by diffractive structures or by an equivalent aspherical surface, possibly approximate.
• the choice of surface, diffractive or aspheric, is related to production costs and other parameters such as chromatic aberrations, which are important with diffractive surfaces. These can be corrected or minimized.
• Creating a beam with a diffractive element can introduce chromatic aberrations, and production tolerances can be critical on parameters such as intensity distributions.
• Using an aspherical surface may be wise.
• the shape of the DPE diffractive structure can be determined by various methods, for example by inverse calculation by defining the range of focal lengths (or powers) sought and then calculating the required phase distribution.
• Z is the axial coordinate on the optical axis; n and r 2 ⁇ are the radial coordinates at the input and at the output on the sampled ⁇ plane.
• the objective of calculating the diffractive DPE structure is to find the phases of this DPE structure that minimize the differences between the effective distribution of the field and that sought, with selected weights.
• the error function is:
• R-- i is the amplitude distribution of the sampled ⁇ th plane. It can be chosen a priori arbitrarily. 5 ⁇ W is a normalized weighting factor.
• phase data are targeted to be continuous (they are modulo 2 ⁇ ) and are converted into geometrical data to define a diffractive surface by the following relation:
• the performances of the diffractive structure DPE and of the hybrid lens obtained by the juxtaposition of this diffractive structure and the basic optical correction element can then be calculated and possibly be optimized with a program of ray tracing such as Zemax (or other ).
• the following parameters are thus obtained: FTM modulation transfer function; image size of a point, "Point-Spread PSF Function", aberrations with Zernike or Seidel coefficients, etc.
• Each of these aspheric surfaces can be positive or negative.
• the optical corrector element can have all kinds of shapes. Combinations such as: convex-concave, concave-convex, convex-convex, concave-concave can also be calculated and constructed.
• the hybrid lens can therefore be positive, negative or have complex shapes for example toric.
• Figure 8 gives an example of the intensity calculated by the method above on a window.
• the DPE phase distribution structure can be calculated in the eye with a model eye, for example that defined in ISO 11979-2, or an appropriate transfer function can be defined.
• the resolution of the pseudophakic eye depends on the definition of the aspherical surface to obtain a negative spherical aberration that will compensate for positive spherical aberration of the cornea.
• the eye-lens system will have a very good resolution / FTM modulation transfer function, limited by the retina and ocular elements, but not by the hybrid lens.
• the hybrid lens gives poor resolution, which is improved after implantation respectively after combination with the visual system.
• the DPE phase distribution structures make it possible to obtain the desired focusing depths.
• the light beam, image side will be a beam of light of almost constant section on a segment.
• the length of this light beam in each segment corresponds to a depth of focus PDF and therefore also to a depth of field PDC chosen.
• Segmentation of focus depths makes it possible to create a bifocal or trifocal lens or more and in general multizone and multifocal. Each segment is independently controllable in depth of focus and intensity. The diffractive / aspherical structure of the zone in question makes it possible to control the desired depth on the segment considered.
• a diffractive DPE / aspherical surface structure may be constructed on an area of the lens, for example on the central portion, to provide a selected focusing depth of the light rays of this region (FIG.
• the diffractive DPE / aspherical surface structure can also be constructed on the peripheral zone of the lens and provide a selected depth of focus of the light rays of this region. This depth of focus may be a diopter fraction, 1 D, or more.
• paraxial and marginal powers are of course in an inverse ratio of focal lengths.
• Focusing depth for near vision can be increased significantly. That of distant vision can often be preserved because it is great. Such a combination will allow a significant depth of focus with only one significant window. This is shown in Figure 6b.
• the intensities in the various zones or windows are dependent on the surfaces of the zones considered and can be chosen.
• the intensity in the near vision zone can be increased at the expense of distant vision.
• the collection of light from the lens depends on its relative openness (focal length / effective diameter). By choosing the size of the different zones, the brightness of the segments is defined. One can be increased at the expense of others as needed.
• the central area may be used to provide a depth of focus of the near-space or far-space images, or conversely the peripheral area may be used to create a depth of focus of near-space images or deep space. All combinations are possible.
• the various zones of the considered face of the lens can also be created slippery, that is to say that starting from the center or the periphery one can create depths of focus for the regions of space more and more distant .
• the various focusing depths are adjustable to obtain variable intensities, for example 40% for a close image and 60% for a distant image or the opposite. Any distribution of intensities is achievable. In general, the distribution intensity between the different areas will be controlled by the relative areas of these different areas. The depth of focus will control separately the intensity distributions of each focal region.
• FIG. 7 gives an example of depth of focus obtained with a diffractive structure of phase distribution alone.
• the abscissas are in m and the intensities on the ordinates are arbitrary.
• Figure 8 illustrates the corresponding intensities as well as the depth of focus of a lens calculated and made with the method presented in this invention. As in the case of Figure 7, in Figure 8, the abscissa are in m and the ordinate intensities are arbitrary.
• near vision For example, to correct the sight of a senior who does not drive or more, vehicle, we can promote near vision at the expense of distant vision with for example 65% of the light in the near segment, which will give a good resolution / FTM in this near field segment which extends from 30 cm to 1 m approximately.
• the intermediate and distant vision will be weaker, but still appreciable.
• 50/50% light distribution will be provided with a close focusing depth at the center of the lens and possibly no depth of focus for distant vision, or even zero power at the periphery since the presbyopic vision is satisfactory at intermediate and distant distance.

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