Diffractive ocular implant with extended near vision

Abstract

The present invention relates to a diffractive ocular implant providing adequate distance vision and enhanced near vision, which is particularly notable for its phase transfer curve as a function of viewing distance (abbreviated PTF-TF) with no discontinuity over a depth of field of at least 1.3D in the corneal plane, advantageously greater than 1.45D. This discontinuity lies between intermediate and near vision, i.e., between 0.5D and 4D for spatial frequencies from 0 to 100 cycles / mm, for a pupil of at least 3 mm in diameter. Figure 3

Description

Title of the invention: Diffractive ocular implant with extended near vision FIELD OF THE INVENTION

[0001] The present invention lies in the field of ocular implants.

[0002] Its subject more particularly is a diffractive ocular implant with extended near vision. TECHNOLOGICAL BACKGROUND OF THE INVENTION

[0003] Cataract is the loss of transparency of the natural lens. The natural lens contributes one-third of the light convergence on the eye. Cataract surgery involves removing the natural lens to restore clear vision. In the 1950s, Mr. Ridley implanted the first intraocular lenses in the sulcus to correct aphakia and thus restore the missing one-third of optical power. Intraocular lenses are now implanted in the capsular bag.

[0004] Without accommodation (at rest), objects located at a far distance are focused (sharp) on the retina of an emmetropic eye (neither myopic, nor hyperopic, nor astigmatic).

[0005] To clearly visualize close objects (from intermediate distance to near distance) the young natural lens has the capacity to deform. Thus, under the action of the ciliary muscles which relax the zonular fibers by contracting, the anterior and posterior radii of curvature of the natural lens increase its optical power by several diopters.

[0006] The loss of this accommodation comes with age and appears in all cases after cataract surgery during which the natural lens is replaced by an artificial lens which does not have the capacity to modify its power according to the desired viewing distance.

[0007] Some so-called accommodative implants (deformable polymers, mobile optics) attempt to restore accommodation, but the results are not satisfactory today (partly because of fibrosis of the capsular bag which, over time, blocks the possibilities of deformation).

[0008] To compensate for this loss of accommodation, many multifocal implants have been developed. They are based on the division of light energy over several vision zones. In the early 2000s, diffractive optics proved their superiority in distance and near vision compared to refractive optics.

[0009] Diffractive optics allow numerous choices of diffraction energy distribution depending on the chosen viewing distances. The optical quality resulting from the The chosen profile is defined by its MTF (modulation transfer function).

[0010] The MTF is a number between 0 and 1 (or 0% and 100%) that represents the contrast of the image (the image may be non-contrasted because it is defocused or because the energy is shared between several foci). The MTF "through focus", abbreviated to MTF-TF, represents the MTF as a function of the defocus (which is represented either as a function of the viewing distance or as a function of the addition (1D=1 / Im)). The MTF-TF is used to determine the depth of field.

[0011] It has been demonstrated in the literature that regardless of the optical profile or technology, visual outcomes are related to the MTF profile of the implanted "1TOL" (acronym for "in-traocular lens" or "implant"). Thus, on average, binocular visual acuity is better than:

[0012] • 0 LogMAR (10 / 10) when the FTM is 0.40;

[0013] • between 0 and 0.05 LogMAR (9 / 10) for an FTM of 0.20;

[0014] • 0.1 LogMAR (8 / 10) for an FTM of 0.15,

[0015] when the MTF is at 3 mm and at 50 cycles / mm, MAR meaning "Minimum Angle Resolution" for "minimum angle of resolution".

[0016] The first diffractive optics were bifocal optics with a peak of MTF for distance vision (Addition 0D) and another peak for near vision (addition +3D or +4D). These implants allow clear vision for reading (around 40 cm) but patients must wear a correction for intermediate vision (between 40 and 90 cm).

[0017] In order to get closer to ideal vision (without glasses correction), with clear and continuous vision at all near vision distances (from 40 to 90 cm), several solutions have been developed:

[0018] - the “Mix & Match”;

[0019] - the “EDOF”;

[0020] - trifocal implants. The "Mix & Match":

[0021] "Mix and Match" involves using two bifocal implants with different additions for each eye (one eye for near vision, the other for intermediate vision).

[0022] The objective is to provide a contrasted image in intermediate vision, which is not the case with trifocal implants. The combinations +1.75D / +4D and +1.5D / +3D (additions in IOL plane) gave interesting "defocus" curves (i.e. visual acuity as a function of viewing distance). But the limit of this solution is the patient's binocular vision comfort. In order to preserve binocular balance, an addition difference of 0.5D was proposed and the combination +2.5D / +3D (additions in IOL plane) showed similar results to trifocals, except in the 1D and 1.5D zone (in the Comaean plane).

[0023] EDOF (acronym for "extended depth of focus" or "extended depth of field"):

[0024] Extended depth of field implants are bifocal (or sometimes trifocal) implants with lower additions to allow good intermediate vision. It should be noted that the lower the addition of an implant, the greater its depth of field will be in distance because the addition is a "1 / x" function of the distance. These implants allow comfort for computer vision (intermediate vision), but it is necessary to wear corrective lenses for near vision. Trifocal implants:

[0025] Trifocal implants are diffractive "IOLs" whose energy is distributed into 3 vision peaks, namely distance, intermediate and near. They therefore provide clear vision and intermediate vision where bifocal implants only provided clear near vision. Currently, trifocal implants are the most advanced "high-end" solution for achieving clear vision from infinity to near.

[0026] But trifocal implants have three distinct vision peaks with a discontinuity in contrast, in the MTF-TF, between near vision and intermediate vision. On some trifocal implants this discontinuity is visible on the MTF-TF at 50 cycles / mm, which represents intermediate letter sizes. Vision is therefore clear at 40 and 80 cm, but not at 60 cm.

[0027] On other implants, we find this discontinuity on the FTM-TF at 100 cycles / mm, that is to say for smaller letter sizes.

[0028] The prior art of interest with respect to the present invention consists of documents FR 3 072 020, US 2007 / 182921 and WO 03 / 107076.

[0029] The objective of the present invention is to overcome the drawbacks indicated above and to propose an intraocular implant which makes it possible to obtain clear and continuous vision over the entire useful near vision zone and requiring the deciphering of small characters (reading a book placed 40 cm from the reader, mobile phone, tablet, laptop placed 60 cm from the user, desktop computer placed 80 cm away, etc.). Summary of the invention

[0030] Thus, the present invention relates to a diffractive ocular implant with correct distance vision and expanded near vision, characterized by the fact that it has a phase transfer curve as a function of the viewing distance (abbreviated PTF-TF) with an absence of discontinuity over a depth of field of at least 1.3D in the corneal plane, that is to say over a range of additions in the corneal plane of at least 1.3D, the addition in the corneal plane being understood as the inverse of the distance between the object seen and the cornea, advantageously greater than 1.45D, which absence of discontinuity is located between intermediate vision and near vision, that is to say between 0.5D and 4D for spatial frequencies of 0 to 100 cycles / mm, this for a pupil of at least 3 mm in diameter and which comprises a body with at least one optical surface having an optical axis and a plurality of diffractive zones arranged concentrically around said optical axis, these concentric zones each having at least one radius r and being distributed between a central region and a peripheral region, this implant being remarkable in that at least one central or peripheral region of said diffractive zones has a profile of N successive ladders whose successive radii, as one moves away from said optical axis, correspond to the relationship:

[0031] [Math.l] rN = ypNXf + 2. A f

[0032] relationship in which:

[0033] N is an integer greater than 1;

[0034] X is the design wavelength;

[0035] fp is the focal length corresponding to the addition for near vision;

[0036] Af is the focal length variation, which is non-zero, positive or negative, and whose value absolute is less than 10000;

[0037] F2(N) is either a polynomial of the variable N of at least order 3, preferably of 3 to 5, which is expressed as follows:

[0038] F2(N)=cte+a.N+b.NA2+c.NA3+d.NA4+---,

[0039] be a function whose limited or Taylor development is equivalent to the polynomial expressed above,

[0040] the height h of said successive ladders (diffractive steps) being given by the relation:

[0041] h=a^- A n

[0042] relationship in which:

[0043] - An is the variation in refractive index, i.e. the difference between the refractive index of the implant material and that of the aqueous humor of the eye or the surrounding environment; - a is the height factor of the ladder, between 0.25 and 1.75.

[0044] Thanks to the invention, depth of field is gained in near vision, while maintaining good distance vision, without discontinuity up to spatial frequencies at 100 cycles / mm.

[0045] The expression "at least of order 3" indicates the minimal order of the polynomial. It is particularly unsuitable to define a maximum order. Indeed, for example, we can consider an equation of order 10, but with a predominant order 3 and negligible coefficients on order 10.

[0046] According to other non-limiting and advantageous characteristics of the invention, taken in isolation or according to any combination of at least two of them:

[0047] - "cte" is a real number between -5 and +5;

[0048] - a, b, c, d, etc. are real numbers between -5 and +5,

[0049] - said diffractive zones have a circular outline;

[0050] - said diffractive zones have an elliptical-shaped contour of which rN is the small radius

[0051] - said diffractive zones are constituted by the alternation of solid zones and empty areas, the latter consisting in particular of slits or holes or of local changes in refractive index;

[0052] - said curve is without discontinuity from 0.8D in the Cornean plane;

[0053] - said curve is without discontinuity from 2D in corneal plane;

[0054] - said region is a central region which has a radius of at least one millimeter and which is surrounded by a refractive or diffractive peripheral region, monofocal or multifocal, for example with a bifocal equation:

[0055] [Math.2] r N = ^NK.f ii

[0056] - said region is a peripheral region, which surrounds a central region, this the latter having a radius of at least one millimeter and being refractive or diffractive, monofocal or multifocal, for example of bifocal equation:

[0057] [Math.3] r v =

[0058] - the function F2(N) a polynomial of the variable N of order 3;

[0059] - the implant is chosen from the following group: intracorneal implant, anterior chamber posterior (phakic or pseudophakic), intraocular posterior chamber or sulcus implant;

[0060] - it has an aspherical surface;

[0061] - it has an apodized profile, that is to say that the height of said ladders decreases as one moves away from the said optical axis, in order to limit the halo phenomenon in night vision.

[0062] Throughout the present application, the expression "correct distance vision" means vision such that the MTF is greater than 20% at 50 cycles / mm over a 3 mm pupil.

[0063] As for the expression "enlarged near vision", its definition is given by the formulation "characterized by the fact that it presents a phase transfer curve as a function of the viewing distance (abbreviated PTF-TF) with an absence of discontinuity over a depth of field of at least 1.3D in the corneal plane, that is to say over a range of additions in the corneal plane of at least 1.3D, the addition in the corneal plane being understood as the inverse of the distance between the object seen and the cornea, advantageously greater than 1.45D".

[0064] Brief description of the drawings

[0065] Other characteristics and advantages of the invention will appear on reading the following description of embodiments of the invention. This description is made with reference to the appended drawings in which:

[0066] [Fig.l] [Fig.l] is a FTM-TF curve of a commercial trifocal implant;

[0067] [Fig.2] [Fig.2] is a commercial bifocal implant FTM-TF curve;

[0068] [Fig.3] [Fig.3] is an FTM-TF curve of an implant according to the invention;

[0069] [Fig.4] [Fig.4] is a view of a "half-profile" of an implant according to the invention, being understood that in this figure, the variability of the scales represented is due to apodization;

[0070] [Fig.5] [Fig.5] is a view of a "half-profile" of an implant according to the invention, being understood that in this figure, the variability of the scales represented is due to apodization;

[0071] [Fig.6] [Fig.6] is an FTM-TF curve of an implant according to the invention;

[0072] [Fig.7] [Fig.7] is an FTM-TF curve of an implant according to the invention;

[0073] [Fig.8] [Fig.8] is an FTM-TF curve of an implant according to the invention. DETAILED DESCRIPTION OF THE INVENTION

[0074] In the following and unless otherwise stated, the addition is indicated corneal plane. Concept of phase transfer function (PTF):

[0075] Any optical system can be represented by its "point spread function" (abbreviated "PSF").

[0076] The PSF represents the spatial distribution of light intensity in the image plane of an optical system, formed from an object source point. The more punctual the PSF, the better the optical quality. This PSF, which is in the spatial domain, is very important because converted into the frequency domain, it is then the "optical transfer function" (abbreviated "OTF") which makes it possible to simulate the image of any object seen through the optics of the system studied.

[0077] It is expressed as follows:

[0078] [Math.4] OTFPSF(x,y) * v' dx dy = Re (OTF (wx, w )) + ilm(OTF )

[0079] Where a,y represent the spatial frequencies in Fourier space, x,y the spatial dimensions in real space and Re and Im the real and imaginary parts of a complex number, i being the square root of -1 in the space of complex numbers.

[0080] The modulation transfer function is the modulus of the optical transfer function, that is, the square root of its real and imaginary parts to the power of 2.

[0081] It is expressed as follows:

[0082] [Math.5] MTF^, w,) = ^Re ( OTF ( w x , m J) 2 + Im ( OTF ( m x , ) J 2

[0083] The phase transfer function PTF is the argument of the optical transfer function. It is expressed as follows:

[0084] [Math.6] -i PTF( w.-. w ) OTF(w x . w ) -MTF(w , ù)} e y>

[0085] To have a comfortable view without discontinuity over a large depth of field, it is interesting to reason in terms of "phase" and "phase inversion". Indeed, when the MTF-TF becomes zero after a peak and then presents a new peak, this often corresponds to a phase inversion, which means that for a given spatial frequency (100 / cycles / mm in the case of an MTF-TF curve at 100 / cycles / mm), the perceptible signal is inverted. Thus, for example, a black test pattern on a white background becomes white on a black background.

[0086] In the case of lOLs, there can be a phase inversion for high frequencies but also depending on the defocus. Thus, for commercial trifocal implants, between intermediate vision and near vision, the implant is no longer sufficiently focused and there is a phase inversion.

[0087] This is the case of [Fig. 1] in which we are dealing with a commercial trifocal implant.

[0088] In this figure, we find, on the abscissa, the addition (from O to 3D in the corneal plane) and on the ordinates the MTF (on the left) and the phase (on the right).

[0089] The following curves were plotted there:

[0090] - curve A: FTM curve;

[0091] - curve B: real part of the OTF curve;

[0092] - curve C: imaginary part of the OTF curve;

[0093] - curve D: phase transfer curve.

[0094] Unless expressly stated otherwise, the figures below use the same parameters.

[0095] We actually observe a phase inversion around the 1.5D addition (in corneal plane). This implant therefore does not allow clear and continuous vision without inversion phase difference between intermediate vision and near vision.

[0096] Definition of the parameters referred to in this application:

[0097] The FTM-TF curves (or TFFTM = "modulation transfer function through focus") represent the quality of the optics (in % - or ratio between 0 and 1-) of contrast of the image for a starting object having a contrast of 100%) as a function of the viewing distance (described in addition in Diopters: 0 D = far vision / +1 to +2D = intermediate addition / 3 D = near addition in corneal plane).

[0098] These are curves simulated with optical simulation software such as that known under the brand name Zemax for intraocular implants placed in an average eye model.

[0099] A FTM-TF curve is established for a given spatial frequency. Usually, for multifocal implants, the FTM-TF at 50 cycles / mm is of interest. FTM-TFs at 25 cycles / mm (coarser objects) and 100 cycles / mm (finer objects) are also of interest.

[0100] A 50 cycles / mm (for example) FTM-TF curve of a given optical profile depends on the pupil of the optical system and the wavelength of the light used.

[0101] Thus, we are preferentially interested in a green wavelength (546nm) but it may also be interesting to plot the photopic MTF-TF corresponding to the integral of the wavelengths of daylight, as well as the scotopic MTF-TF (night vision).

[0102] Similarly, we are preferentially interested in a pupil of 3 mm in diameter (corresponding to well-lit vision (reading and day vision), but the continuity of FTM-TF can be interesting for pupils of 2 to 6 mm.

[0103] A FTM value greater than 0.15 is considered to provide satisfactory near vision to the wearer.

[0104] Near vision, VP, is typically equal to +3D (in addition to the corneal plane), but can be between +2D and +4D.

[0105] Intermediate vision, VI, is typically equal to +1.5D (in corneal plane addition), but can be between +1D and +2D.

[0106] Implants according to the invention:

[0107] The constant phase widened near vision implants according to the invention can be defined as follows:

[0108] These are diffractive implants having far vision and near vision whose phase of the optical transfer function is constant over an extended intermediate to near vision zone, i.e. without phase inversion up to a spatial frequency of 100 cycles / mm, this optical transfer function being constant over a range of addition values ​​which is at least 30% (and preferably 45%) wider than that of a conventional bifocal implant, such as that called ARtis PL M, com- sold by the present depositor.

[0109] In the attached [Fig.2] is represented the phase transfer function at 100 cycles / mm depending on the addition for a “classic” bifocal implant with +3 D ​​addition.

[0110] We note that the phase is constant (curve D) over the zone 1.35 D to 2.3 5D, i.e. over a depth of 1 D in the corneal plane.

[0111] An example of a constant phase widened near vision profile of an implant according to the invention is shown in [Fig.3].

[0112] We note that the phase is constant over the zone 0.6D to 2.05 D, or over a depth of 1.45D in the corneal plane.

[0113] Such curves can be obtained from different diffractive optical implants, which will be described below.

[0114] It is obviously considered that an implant of this type comprises a body with at least one optical surface having an optical axis and a plurality of diffractive zones arranged concentrically around this optical axis, these concentric zones each having at least one radius r.

[0115] For a bifocal implant, the radii of the successive rings have a radius rN such that:

[0116] [Math.7]

[0117] relationship in which:

[0118] - N is the number of the ring (counted from the center); - fp is the focal length corresponding to the addition for near vision - X is the design wavelength (typically 546 nm).

[0119] The height h of the diffractive steps (ladders) of the zones is:

[0120] [Math.8] 11 a A n

[0121] relationship in which:

[0122] - An is the variation in refractive index (i.e. the difference between the refractive index of the implant material and that of the aqueous humor of the eye, or of the surrounding environment when it is an intracomeal implant); - a is the profile height factor.

[0123] If a=0.5, then the relative energy distribution is 50% for distance vision and 50% for near vision.

[0124] The shape of the diffractive echelons of each zone is called "kinoform" and is described by a parabola on each echelon such that:

[0125]

[0126]

[0127]

[0128]

[0129]

[0130]

[0131]

[0132]

[0133]

[0134]

[0135]

[0136]

[0137]

[0138]

[0139]

[0140]

[0141] [Math.9] - r2 - x2 Prof il (x) = « -2^2— Where x is the radial position. According to the invention, an implant having a continuous phase profile between near vision and intermediate vision is produced by using diffractive profiles giving an extended depth of field. The central zone of such an implant is defined by a profile whose radius of successive rings rN is fixed by an equation of the type: [Math. 10] r N = ^NTf + 2. A f expression in which F2(N) is a polynomial of variable N of minimum order 3. F2(N) can have as expression [Math. 11] F2(N) = cte + a. N + b. N 2 + c. N 3 + dN 4 + ... Or : - N is an integer greater than 1; - X is the design wavelength; - fp is the focal length corresponding to the addition for near vision; - Afest the focal variation; - cte is a constant consisting of a real number between -5 and +5; - a, b, c and d are real numbers between -5 and +5. Note that F2(N) can be a function whose limited or Taylor expansion is equivalent to the polynomial expressed above. By the term "equivalent" we mean that the limited or Taylor expansion of said function gives the same result as the function F2(N) expressed above. For purely indicative purposes, these implants may include a central region (for example, 1.5 to 6 mm in diameter) with extended depth of field and possibly a “peripheral” zone region that can be described as classic (for example, 2 to 6 mm in diameter). In [Fig.4] is shown the "half" profile of an implant II in accordance with the present invention. By "half" profile, we mean the fact that the ordinate axis, which translates the height of the scales of these implants in micrometers, is merged with their optical axis AO and that we have represented only the profile which extends on one side of this axis. In this figure, the said central and peripheral regions are respectively referenced RC and RP.

[0142] It will be noted here that the profile of the fourth ladder visible in this figure has been cut, due to the beginning of the peripheral region RP.

[0143] Although “kinoform”, the ladders could have a different shape (sine, cosine for example), this different shape not drastically modifying the present invention.

[0144] In the case presented here, the different diffractive zones have a circular outline. However, according to alternative embodiments, not shown here, these diffractive zones have an elliptical-shaped outline of which rN is the small radius.

[0145] Still according to the embodiment presented here, the central region RC has an extended depth of field, has a radius of at least one millimeter and is surrounded by a peripheral region RP refractive or diffractive, monofocal or multifocal, for example of bifocal equation:

[0146] [Math. 12] rN =

[0147] Conversely, it could be the opposite, so that it would be the central region RC, having a radius of at least one millimeter, which would be refractive or diffractive, monofocal or multifocal, for example with a bifocal equation:

[0148] [Math. 13] £7 W — V

[0149] In [Fig.5] is shown the "half-profile" of another implant 12 according to the present invention.

[0150] The main parameters of implants according to the invention are given below.

[0151] Example 1:

[0152] Function F(N) of order 4 (which corresponds to the profile of [Fig.5] and to the curves of [Fig.6]):

[0153] [Tables 1] Central region: rings 1 to 4 1000 / 3.05 CX 0.5 A f 800 Peripheral region: rings 6 to 12 f? p2 1000 / 2.77 ex 0 0.5 Central region:

[0154] •

[0155]

[0156]

[0157]

[0158]

[0159] [Math. 14] = ^2 X .N. f + 2 X.( ). A , “ p 1 \ \ 3 / / / [Math. 15] Profile^x^ « • Peripheral region: [Math. 16] = aWMGJ [Math. 17]

[0160]

[0161]

[0162]

[0163] As can be seen in [Fig.6], the phase is constant over the area from 0.5D to 2.05, i.e. over a depth of 1.55D in the Cornean plane. Example 2 (which corresponds to the profile of [Fig.4] and the curves of [Fig.7]) Function F(N) of order 5: [Tables 2] Central region: rings 1 to 4 1000 / 3.05 tx J 0.5 A / 1400 Peripheral region rings 6 to 12 / . 1000 / 2.77 “ 2 0.5 central region:

[0164]

[0165] [Math. 18] rk = ^2 X .N. f + 2 XA , 1| pl \ XD / / J

[0166] [Math. 19] Profile (x) =

[0167]

[0168] • peripheral region: [Math.20]

[0169] [Math.21] Prof il {x) = o< 2" n 2 ? At r2 N -x~

[0170] As can be seen in [Fig.7], the phase is constant over the zone from 0.5D to 2.14D, i.e. over a depth of 1.64D at the Cornean plane.

[0171] Finally, in the embodiment of [Fig.8], the phase is constant over the area from 1.1D to 3.3D, i.e. over a depth of 2.2 in the Cornean plane.

[0172] As indicated above, the diffractive profiles (also called steps or ladders) of the implants according to the invention can be apodized (that is to say that we are dealing with a reduction in the height of the steps between the center and the periphery) as a function of the radius (which constitutes the variable x), according to the following equation:

[0173] Apodized Profile (x) = Profile (x) * Apodization(x)

[0174] The function “apodization(x)” is a decreasing function such that, for 0 <abs(x)<r max="rayon" (r maximal du profil diffractif), alors 0<apodisation(x) <1.

[0175] For example, this function can take the following form: Apodization (x) = (1- abs (ax / b)Ac) with a, b and c consisting of real numbers.

[0176] The diffractive profile may be composed of concentric, circular or oval diffractive steps (echelettes). In other embodiments the diffractive effect may be obtained by alternating solid zones and empty zones (holes, slits), which modifies the local refractive index by zones and generates diffraction in the same way as the echelettes.

[0177] Expressed differently, this diffractive profile can be defined not by a geometric shape, but by a variation in the refractive index of the material(s) that compose it and that will create the same effect. The modification of the refractive index can for example be obtained by alternating solid zones with the index "n mat" and empty zones with the index "nO" (made up of holes, slits), which modifies the local refractive index by zones and generates diffraction in the same way as the echelettes.

[0178] The implants according to the invention make it possible to correct presbyopia. They can also make it possible to correct other ametropias (myopia, hyperopia, astigmatism).

[0179] These may be intraocular implants (lenticules), anterior chamber (phakic or pseudophakic), or intraocular posterior chamber or sulcus).

Claims

Claims

1. Diffractive ocular implant with correct distance vision, i.e. vision such that the modulation transfer function (MTF) of said implant is greater than 20% at 50 cycles / mm on a 3mm pupil, and with enlarged near vision (II, 12), i.e. with an absence of discontinuity in its phase transfer curve as a function of the viewing distance (abbreviated PTF-TF) characterized by the fact that: - it has a phase transfer curve as a function of viewing distance (abbreviated PTF-TF) with an absence of discontinuity over a depth of field of at least 1.3D in the corneal plane, i.e. over a range of additions in the corneal plane of at least 1.3D, the addition in the corneal plane being understood as the inverse of the distance between the object seen and the cornea, advantageously greater than 1.45D, which absence of discontinuity is located between intermediate vision and near vision, i.e. between 0.5D and 4D for spatial frequencies of 0 to 100 cycles / mm, this for a pupil of at least 3 mm in diameter; - it comprises a body with at least one optical surface having an optical axis (AO) and a plurality of diffractive zones arranged concentrically around said optical axis (AO), these concentric zones each having at least one radius r and being distributed between a central region (RC) and a peripheral region (RP), at least one central region (RC) or peripheral region (RP) of said diffractive zones having a profile of N successive ladders whose successive radii rN, as one moves away from said optical axis (AO), correspond to the relationship: rN — ^2 NA f + 27^.^2^^, A relation in which: N is an integer greater than 1; X is the design wavelength; fp is the focal length corresponding to the addition for near vision Afest the focal length variation, which is non-zero, positive or negative, and whose absolute value is less than 10000; ; F2(N) is a polynomial of the variable N of order between 3 and 5, which is expressed as follows: "1 2 4 F2 (N) = cte + a. N+h. N~ + c. N' + dN + ,., ; - the maximum height of said successive ladders, that is to say of the diffractive steps, namely the difference between two successive steps, is given by the relation:

1. _ a ^X relationship in which: An is the variation in refractive index, i.e. the difference between the refractive index of the implant material and that of the aqueous humor of the eye or the surrounding environment; a is the height factor of the scale, between 0.25 and 1.

75.

2. Implant (II, 12) according to claim 1, characterized in that "cte" is a real number between -5 and +5.

3. Implant (II, 12) according to claim 1 or 2, characterized in that a, b, c, d, etc. are real numbers between -5 and +5.

4. Implant (II, 12) according to one of claims 1 to 3, characterized in that said diffractive zones have a circular outline.

5. Implant (II, 12) according to one of claims 1 to 3, characterized in that said diffractive zones have an elliptical-shaped contour of which rN is the small radius.

6. Implant (II, 12) according to one of claims 1 to 3, characterized in that said diffractive zones are constituted by the alternation of solid zones of index “nmat” and empty zones of index “nO”, said empty zones consisting of slots or holes.

7. Implant (II, 12) according to one of claims 1 to 6, characterized in that said curve is without discontinuity from 0.8D in the corneal plane.

8. Implant (II, 12) according to one of claims 1 to 6, characterized in that said curve is without discontinuity from 2D in corneal plane.

9. Implant (II, 12) according to one of claims 1 to 8, characterized in that said region is a central region (RC) which has a radius of at least one millimeter and which is surrounded by a peripheral region (RP) which is refractive or diffractive, monofocal or multifocal, for example with a bifocal equation: rN = ^2 NX . f .

10. Implant (II, 12) according to one of claims 1 to 8, characterized in that said region is a peripheral region (RP), which surrounds a central region (RC), the latter having a radius of at least one millimeter and being refractive or diffractive, monofocal or multifocal, for example of bifocal equation: .

11. Implant (II, 12) according to one of claims 1 to 10, characterized in that the function F2(N) is a polynomial of the variable N of order 3.

12. Implant (II, 12) according to one of the preceding claims, characterized in that it is chosen from the following group: intra-coma implant, anterior chamber implant (phakic or pseudophakic), intraocular posterior chamber implant or sulcus implant.

13. Implant (II, 12) according to one of the preceding claims, characterized in that it has an aspherical surface.

14. Implant (II, 12) according to one of claims 1 to 5 and 7 to 13, characterized in that it has an apodized profile, that is to say that the height of said steps decreases as one moves away from said optical axis, in order to limit the halo phenomenon in night vision.

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