EP2806827A2

EP2806827A2 - Improved intraocular lens and corresponding manufacturing method

Info

Publication number: EP2806827A2
Application number: EP13704186.9A
Authority: EP
Inventors: Frédéric Hehn
Original assignee: Individual
Current assignee: Individual
Priority date: 2012-01-24
Filing date: 2013-01-22
Publication date: 2014-12-03
Also published as: CO7010812A2; AU2013213472A1; US20150297343A1; CA2861746A1; BR112014017990A2; BR112014017990A8; MX2014008923A; RU2014129644A; JP2015504752A; WO2013110888A3; WO2013110888A2; CN104203154A; KR20140119143A; FR2985900A1

Abstract

The invention relates to an intraocular lens having an optical axis, and a central area and a peripheral area which are substantially symmetrical relative to said optical axis and extend substantially perpendicular thereto, said central area extending up to a first distance, and the peripheral area extending from the first distance until the end of the intraocular lens, wherein the central area has nominal optical power, and the peripheral area has a radius of curvature that varies in a continuous, monotonic manner in accordance with the distance to the optical axis, such that a target asphericity value is obtained at a second distance from the optical axis, the first distance and the second distance being calculated from a photopic pupil diameter and a mesopic pupil diameter of a patient, respectively.

Description

Improved intraocular lens and method of manufacture thereof

The invention relates to the field of ophthalmology, and more particularly intraocular lenses.

The field of intraocular lenses has seen many discoveries and progress over the past ten years. Indeed, the treatment of cataract has become a classic and controlled operation. However, this field remains a field at the forefront of research, and in which the maturity of the methods remains relative. This is reflected in particular by the fact that there is currently no intraocular lens that can correct both myopia (or hyperopia) and presbyopia satisfactorily. Indeed, the only implants that aim to solve this problem are multifocal lenses, which are sources of halos that can be very troublesome.

The invention improves the situation.

For this purpose, the invention proposes an intraocular lens, characterized in that it has an optical axis and a central zone and a peripheral zone substantially symmetrical with respect to said optical axis and extending substantially perpendicular thereto, said zone central region extending to a first distance, and the peripheral zone extending from the first distance to the end of the intraocular lens, in which the central zone has a nominal optical power, and the peripheral zone has a a radius of curvature that varies continuously and monotonically as a function of the distance to the optical axis, so that a target asphericity value is obtained at a second distance from the optical axis, the first distance and the second distance being calculated from a photopic pupil diameter and a mesopic pupil diameter of a patient, respectively.

The invention also relates to a method for calculating a radius of curvature profile for an intraocular lens which comprises the following steps: receiving biometric parameters of a patient comprising at least a first radius of curvature, a photopic pupil diameter, and a mesopic pupil diameter,

determining an emmetropia distance from at least the mesopic pupil diameter, and a second radius of curvature from the first radius of curvature and a target asphericity value,

calculating a radius of curvature profile in a direction substantially perpendicular to a desired optical axis for the intraocular lens, wherein the radius of curvature is equal to the first radius of curvature in a central zone extending between the optical axis and a first distance calculated from at least the photopic pupil diameter, and wherein, in a peripheral zone extending from the first distance to the end of the intraocular lens, the radius of curvature varies continuously and monotonically as a function of from the distance to the optical axis, so that the radius of curvature is equal to the second radius of curvature at the distance of emmetropy with respect to the optical axis.

Other features and advantages of the invention will appear better on reading the following description, taken from examples given for illustrative and non-limiting purposes, taken from the drawings in which:

FIG. 1 represents an optical diagram of an eye,

FIG. 2 represents three keratometric profiles of an eye,

FIG. 3 represents a schematic view of an eye in which an intraocular lens according to the invention is implanted, and in which the pupil is dilated to the maximum,

FIG. 4 represents a schematic view of an eye in which an intraocular lens according to the invention is implanted, and in which the pupil is moderately dilated,

FIG. 5 represents a schematic view of an eye in which an intraocular lens according to the invention is implanted, and in which the pupil is dilated to a minimum, FIG. 6 represents a profile of radius of curvature of the lens of FIGS. 3 to 5,

FIG. 7 represents a profile of curvature radius profile of an alternative embodiment of an intraocular lens according to the invention,

FIG. 8 represents a profile of the radius of curvature of an alternative embodiment of an intraocular lens according to the invention,

FIG. 9 represents an exemplary flow diagram of a method for manufacturing an intraocular lens according to the invention, and

- Figure 10 shows a diagram of a device for calculating an intraocular lens profile according to the invention, which can be implemented in the method of Figure 9.

The drawings and the description below contain, for the most part, elements of a certain character. They can therefore not only serve to better understand the present invention, but also contribute to its definition, if any.

In addition, the detailed description is augmented by Appendix A, which gives the formulation of certain mathematical formulas implemented in the context of the invention. This Annex is set aside for the purpose of clarification and to facilitate referrals. It is an integral part of the description, and can therefore not only serve to better understand the present invention, but also contribute to its definition, if any.

Figure 1 shows an optical diagram for modeling the vision in an eye. An eye 2 comprises a cornea 4, a pupil 6, a lens 8 and a retina 10.

The cornea 4 and the lens 8 act as lenses that concentrate the light rays, the pupil 6 acts as a diaphragm, and the retina as the photoreceptor. Ideally, the cornea 4 is prolate, and has a spacing with the retina 10 such that all images are formed in a focused manner on the latter (zero spherical aberrations). This is not usually the case. As can be seen in Figure 2, there are three main types of corneal profiles:

the prolate profile, for which the keratometric index is slightly greater at the center than at the periphery, which induces an asphericity Q <0, with simple line hatching in FIG. 2,

the spherical profile, for which the keratometric index is constant on the eye (Q = 0), and

the oblate profile, for which the keratometric index is slightly lower than the center than at the periphery, which induces an asphericity Q> 0, with double hatching in FIG.

In general, a prolate or slightly hyper-prolate profile is preferred because it allows a better near vision. An oblate profile is penalizing for distant vision, especially at night. The lens 8 complements the cornea 4, and undergoes deformations to allow accommodation for near vision and far vision. In fact, the cornea 4 and the crystalline lens 8 can be seen as a focusing assembly 12 whose profile is generally prolate, spherical or oblate. Myopia and hyperopia are two ophthalmological conditions that result in a distorted vision. In the case of myopia, the eye is too long, and the retina 10 is disposed after the focal plane of the focusing assembly. As a result, the rays corresponding to the distant images are not focused correctly and the distance vision is not clear. In the case of hyperopia, the opposite is true: the eye is too short. However, in this case, accommodation of the crystalline lens may partially compensate for this defect. Another ophthalmological condition is presbyopia.

As people age, or as a result of some trauma, lens 8 may experience progressive opacification, which is also known as cataract. In addition, at around age 40, the human eye gradually loses its ability to accommodate (contract) to deform the lens, which is necessary for near vision development (loss of vision). 'accommodation). Cataract is a condition that has been known since antiquity and is very well treated today by means of a surgical procedure in which lens 8 is replaced by an intraocular lens or implant. In order to take into account pre-existing sight problems in the patient, various types of implants have been developed, in particular to correct myopia or hyperopia. Nevertheless, these implants result in a significant loss of quality with regard to near vision. The situation is even worse when the focus assembly has an oblate profile. To compensate for presbyopia, it is possible to add a magnifying glass, but this is embarrassing. It therefore appears that it is not possible today to treat myopia and presbyopia with an intraocular lens, or even to treat one of the two in isolation without penalizing either distant vision or vision. from close. The only intraocular lenses that exist for this purpose are called "diffractive multifocal", use the principle of the Augustin Fresnel lens (1788-1827) described in 1822, a principle which, apart from apodization, has hardly been improved. .

This type of lens includes a plurality of "steps", each step acting like a prism that separates the light by means of two foci: one for far vision, and the other for near vision. . Since the lens must be in one piece, the prisms are interconnected by a portion of continuity, and this dichotomy induces annoying light halos, a loss of contrast, and / or a significant deficit in the intermediate vision.

Other methods include using an intraocular lens treating near vision for one eye, and an intraocular lens treating distant vision for the other eye. These treatments perform a flip-flop called monovision. However, this does not give satisfactory results.

The Applicant's work led him to study the corneal profiles for their laser treatment. Specifically, the Applicant has discovered that a corneal profile can be calculated to treat problems related to near vision without affecting vision from a distance.

A simplified explanation is that this treatment will produce a corneal profile worked mainly on the periphery, with a slightly prolate eye. The resulting asphericity is used advantageously to improve near vision, while distant vision is not affected because it is mainly exercised in the center of the eye. This process is called "advanced isovision", and allows each eye to have excellent vision, both refractively and near-aspherically, which is opposes to monovision.

Indeed, if we refer to the polynomials of Zernike:

the far vision is corrected refractive manner by modifying the coefficient C4, or Z (2.0) called ¹ belonging defocus on the ^2nd order polynomial, and

the intermediate and near vision will be corrected aspherical way, thanks to the negative asphericity of the cornea inducing negative spherical aberration coefficient C12 or Z (4.0) called ^2nd defocus belonging to the 4th order polynomial.

It is therefore possible to use two types of optical corrections, far and near respectively, which use different polynomial orders, respectively of two level Z (2, 0) of polar equation (2p ² - 1), and of level four Z (4, 0) of polar equation (6p ⁴ - 6p ² +1). These corrections are not in competition, but are instead complementary.

Such an optical system does not divide the light in half, and allows to reach a vision 20/20 Jl in monocular, without compromise neither in distant vision, in near vision, or in intermediate vision, and without loss of contrast . By pushing this research, the Applicant has extended its work to intraocular lenses, including how they can be profiled to treat both near vision and far vision. FIG. 3 represents an axial schematic view of an eye in which an intraocular lens 12 according to the invention has been implanted.

As will be seen in what follows, the profile of the intraocular lens 12 depends on the corneal profile of the eye 2, as well as the general characteristics of his eye, such as its length, etc. As will also appear, the profile of the intraocular lens 12 depends on a parameter called "useful optical area".

Indeed, when implanted, the intraocular lens 12 comes into practically contact with the pupil 6, as the natural lens 8 which is usually located in the posterior chamber, at a short distance from the pupil 6 of about 100 μιη. Due to its positioning against the pupil 6, only a restricted portion called useful optical zone will be traversed by light rays.

The useful optical zone of the intraocular lens 12 depends directly on the state of dilation of the pupil 6. Indeed, the more it is dilated, the larger the useful optical area.

In Figure 3, the pupil 6 has been shown in its state of maximum dilatation, or scotopic pupil. In this configuration, the pupil diameter is noted Ps. In FIG. 4, the pupil 6 has been shown in its average dilation state, or mesopic pupil. In this configuration, the diameter of the pupil is noted Pm. In Figure 5, the pupil 6 has been shown in its state of minimal expansion, or photopic pupil. In this configuration, the pupil diameter is denoted Pp. Each of these states can be approximated to a view condition. Indeed, when it is dark, the light is minimal, and the pupil 6 will be dilated between Pm and Ps. Conversely, in daylight, the light is maximum, and the pupil 6 will be dilated. between Pm and Pp. For fairly obvious reasons, the reading is generally associated with the latter case, that is to say when the pupil 6 is dilated between Pm and Pp. Therefore, the intraocular lens 12 has a profile. Optimized to work between Pm and Pp. Before a cataract operation, the patient is subjected to various tests, also called biometrics. Biometrics is performed to determine a parameter of the intraocular lens called power. This parameter is used in particular to choose an implant adapted to the structure of the patient's eye, and allows for example to correct its vision from afar.

In fact, the power of the implant is based on its anterior and posterior radii of curvature, its thickness, and its refractive index n. The index n is specific to the material which composes the implant, and is determined with respect to a saline solution of refractive index 1.336, at 35 ° C, for a wavelength of 546.1 nm which corresponds to the average wavelength of the spectrum perceived by the human eye.

This power is estimated on an optical zone of 3 mm in diameter. The radius of curvature at the center of the intraocular lens 12 corresponding to this nominal power will be noted Rc in the following. The power can be calculated for example by means of a SRK-type formula, which calculates it from an implant-dependent constant A, the length L of the eye, and the central keratometric index of the cornea. of the patient.

Many other formulas can be used to calculate the power according to the particular therapeutic indications of each patient, and thus to obtain the equivalent radius of curvature Rc. Once the nominal power is determined, the radius of curvature Rc is fixed since it is the radius of curvature at the center of an intraocular lens that has the nominal power. In the course of this work on laser surgery, the Applicant has discovered that, in order to obtain simultaneous treatment of myopia / hyperopia and optimal presbyopia, it is necessary to obtain a central index for the focusing assembly that corrects the myopia / hyperopia, and modulate the eccentric profile with respect to the optical axis so as to obtain an asperity value Q which depends on the age of the patient. This is described in the French patent application FR 11/02842. In this case, as the intraocular lens is replacing the lens, there is no more accommodation at all. The target asphericity is therefore fixed, and can take a necessary and sufficient value such as -1.0. And as we saw above, this target value of asphericity must be obtained for the mesopic pupil. The Applicant has therefore created intraocular lenses whose profile of radius of curvature is such that, in a central zone, the power of the intraocular lens is the nominal power derived from the biometry and which corresponds to the radius of curvature Rc, and in a peripheral zone, at a distance corresponding to the mesopic pupil, the radius of curvature is such that the asphericity is -1.0. In general, the distance at which the asphericity obtained must be equal to -1.0 will be called the emmetropia distance and denoted by De.

As will be seen below, the distance De is an important parameter for the intraocular lens, since it indirectly defines its profile of radius of curvature. In general, the distance De depends on the mesopic pupil Pm. As a variant, the distance De can be calculated from a function having as its argument the mesopic pupil Pm, as well as the photopic pupil Pp and / or the scotopic pupil Ps. In the examples described with FIGS. 6 to 8, the distance De is equal to Pm 2. In the following, the distances, whether Ps, Pm, Pp or De, or other distance, are given in mm, along the x axis, which is perpendicular to the axis optical y.

In Figures 6 to 8, the profiles shown are based on the following parameters:

Pp = 1 mm,

De = Pm 2 = 3 mm,

Rc = 23 diopters,

Rp = 17 diopters, and

a = 0.5. FIG. 6 represents a first profile of preferred radius of curvature for an intraocular lens according to the invention.

In this embodiment, the radius of curvature of the intraocular lens 12 varies according to four zones denoted respectively ZI, Z2, Z3 and Z4.

In the example described here, the zone ZI comprises the part the intraocular lens along the x axis which is in the range [-Pp / 2; Pp / 2]. In fact the zone ZI corresponds to the zone of the intraocular lens which is useful for distant vision. In the zone ZI, the radius of curvature of the intraocular lens is equal to the radius of curvature Rc. Thus, vision from afar is assured.

In the example described here, the zone Z2 comprises the portion of the intraocular lens which is included along the x axis in the ranges [-From; -Pp / 2] and [Pp / 2; De], i.e., [-Pm / 2; -Pp / 2] and [Pp / 2; Pm / 2]. In fact, the zone Z2 corresponds to the zone of the intraocular lens 12 which is between the photopic pupil Pp and the mesopic pupil Pm, that is to say the zone which is useful for reading or near vision in general. . As we saw above, the aim is that the asphericity Q is equal to -1.0 at the distance De. For this, it is necessary that the intraocular lens has a radius of curvature Rp that we can calculate from formula [10] of Annex A.

In zone Z2, the radius of curvature of the intraocular lens is therefore equal to Rc for x equal -Pp / 2 and to Pp / 2, and to Rp for x equal to -Pm / 2 and Pm / 2. Between these values, the Applicant has discovered that it is advantageous for the radius of curvature of the intraocular lens in zone Z2 to evolve according to formula [20] of Appendix A. In fact, this profile makes it possible to obtain the desired asphericity in a progressive way. In the example described here, the zone Z3 comprises the portion of the intraocular lens which is included along the x axis in the ranges [- (2De-Pp / 2); -From] and [De; (2De-Pp / 2)], i.e., [- (Pm-Pp / 2); -Pm / 2] and [Pm / 2; (Pp-Pm / 2)]. In fact zone Z3 corresponds to the zone of the intraocular lens which is between the photopic pupil Pm and the scotopic pupil Ps, that is to say the area of the pupil which is used for night vision.

The Applicant has discovered that it is advantageous for the radius of curvature of the intraocular lens in zone Z3 to evolve according to formula [30] of Appendix A. In fact, this harmonises the profile of the intraocular lens with zone Z2. .

Finally, zone Z4 comprises, in the example described here, the portion of the intraocular lens which is included along the x axis in the ranges [-6.5; - (2De-Pp / 2)] and [(2De-Pp / 2); 6.5], i.e., [-6.5; - (Pm-Pp / 2)] and [(Pm-Pp / 2); 6.5]. In fact, zone Z4 corresponds to the portion of the intraocular lens that is not exposed to light.

The Applicant has discovered that it is advantageous for the radius of curvature of the intraocular lens to be 2Rp-Rc in zone Z4, ie the radius of curvature of the intraocular lens at the end of zone Z3.

FIG. 7 represents another embodiment of the intraocular lens according to the invention. In this embodiment, the Applicant has considered that the progression in the zone Z3 should be decreased, so that the asphericity does not decrease too much. The zones ZI to Z4 and the values Rc and Rp have not been represented because they are identical to those of FIG.

For this, the radius of curvature of the intraocular lens in the zone Z3 changes according to the formula [30] of Annex A, where the coefficient a is a real within the range] 0; 1 [, and chosen in this range, for example according to a ratio C of the formula [40] of Appendix A. In order to preserve the continuity, the radius of curvature of the intraocular lens in zone Z4 is identical to the radius of curvature of the intraocular lens at the end of the zone Z3, that is to say that it is greater than in the case of FIG. 6. In practice this value is equal to (l + a ) Rp-Rc. FIG. 8 represents yet another embodiment of the intraocular lens according to the invention. In this embodiment, the Applicant has simplified the radius of curvature profile of the intraocular lens, so that:

the radius of curvature in zones ZI and Z4 is identical to that of the lens of FIG. 6,

the radius of curvature evolves linearly in zones Z2 and Z3, and

the radius of curvature is equal to Rp for x equal to De and -De, that is to say -Pm / 2 and Pm / 2. As a variant of this embodiment, zone Z3 and zone Z4 may be fused, and have a radius of curvature equal to Rp, for the same purpose as that pursued with the embodiment of FIG. 7. For the sake of simplicity zones Z1 to Z4 and the values Rc and Rp have also not been shown in this figure. In the foregoing embodiments, the ZI area may be expanded or decreased in width, and the Z3 area may also be expanded or deleted until it merges with the Z2 area or the Z4 area. Zone Z4 can also be delimited not by the value x equal to 2De - Pp / 2, but by the value x equal Ps. In this case, the formulas of Annex A will be adapted. Finally, functions other than the cos () function can be used. It is particularly apparent from these embodiments that the radius of curvature can be described by a continuous mathematical function whose values are between Rc and Rp at least.

FIG. 9 represents a schematic flow diagram of a method of manufacturing an intraocular lens according to one of the preceding embodiments.

This method begins with an operation 900 in which parameters concerning the patient are received. These parameters are the desired radius of curvature Rc at the center of the intraocular lens or the corresponding nominal power, as well as at least the distances Pp and Pm of the patient. Alternatively, the distance Ps can also be received. Then, in an operation 910, the emmetropia distance De is calculated, either by defining it equal to Pm / 2, or by a function of the distances Pm, as well as Pp and / or Ps. The operation 910 also comprises the calculation a radius of curvature Rp which makes it possible to obtain an asphericity value of -1.0 at the distance -De / 2 and De / 2.

Once the operation 910 is completed, the radius of curvature profile of the intraocular lens is calculated in an operation 920, according to one of the profiles described with FIGS. 6 to 8, and by definition of the different zones ZI to Z4. Finally, in an operation 930, the intraocular lens is manufactured according to the profile calculated in step 920.

It appears that the method of FIG. 9 comprises a method for calculating the radius of curvature profile of an intraocular lens and a manufacturing step based on this profile.

FIG. 10 represents a simplified diagram of a device for calculating the radius of curvature profile of an intraocular lens according to the invention. The device 20 comprises a memory 24, a processing unit 26, an interface 28 and a scheduler 30.

The memory 24 is in the example described here a conventional storage medium, which can be a hard disk tray or flash memory (SSD), flash memory or ROM, a physical storage medium as a compact disc (CD ), a DVD disc, a Blu-Ray disc, or any other type of physical storage medium. The storage unit 24 can also be deported, on a network storage medium (SAN), or on the Internet, or generally in the "cloud". In the example described here, the processing unit 26 is a software item executed by a computer that contains them. However, it could be performed in a distributed manner on several computers, or be in the form of a printed circuit (ASIC, FPGA or other), or a dedicated microprocessor (NoC or SoC) to one or more cores.

The interface 28 allows a practitioner to enter the biometric parameters relating to a patient for whom the radius of curvature profile calculation is desired, and to adjust some of these parameters if necessary. The interface 28 may be electronic, that is to say be a link between the device 20 and another device allowing the practitioner to interact with the device 20. The interface 28 can also integrate such a device, and understand for example a display and / or speakers, to allow communication with the practitioner.

The scheduler 30 selectively controls the processing unit 26 and the interface 28, and accesses the memory 24 to implement the processes of the method of FIG. 9. It follows from the foregoing that the Applicant has discovered a lens intraocular whose profile radius of curvature can treat both myopia / hyperopia, astigmatism_and presbyopia. This is obtained by the definition of a continuous and monotonous radius of curvature profile (strictly or in the broad sense) which associates two values of radius of curvature (Rc and Rp) one of which (that corresponding to Rc) corresponds to a nominal optical power determined in a conventional manner.

Thus, the radius of curvature profile comprises a central zone (ZI) in which the optical power is nominal, and a peripheral zone (Z2, Z3, Z4) in which the optical power varies, so that a target value of asphericity (-1.0) is obtained at a selected distance (De) from the optical axis. In the peripheral zone, the zone Z2 can be seen as an emmetropia zone, the zone Z3 as an intermediate zone, and the zone Z4 as an end zone, the zones Z3 and Z4 defining between them an external zone. Unlike diffractive lenses, the profile thus defined does not require a solution of continuity or step, and therefore does not induce halos or loss of contrast. Indeed, spherical aberrations produced are like a property added to the refractive characteristic, given by the central power of the implant, and they are created by the peripheral lowering of the radius of curvature of the implant. This is especially achieved through the use of optical effects not used in known intraocular lenses. Indeed, until the discovery of the Applicant, it was considered that only Zernicke polynomials of order 2 were exploitable.

Note that the lens of the invention has been described in order to obtain an asphericity equal to -1.0 at the second distance. In the more general case, if a different target asphericity value is desired, it is sufficient to change the value of the radius of curvature Rp to the second distance, according to the formula [50] of Annex A.

In different variants, the device may have the following characteristics: the peripheral zone (Z2, Z3, Z4) comprises an emmetropia zone (Z2) extending between the first distance (Pp / 2) and the second distance ( De), in which the radius of curvature varies continuously and strictly monotonically in the emmetropia zone (Z2),

the radius of curvature varies as a function of the distance to the optical axis according to an at least partly trigonometric function ([20]) in the emmetropia zone (Z2). the radius of curvature varies linearly as a function of the distance to the optical axis in the emmetropia zone (Z2),

the peripheral zone (Z2, Z3, Z4) comprises an external zone (Z3, Z4), extending beyond the second distance (De), in which the radius of curvature varies continuously and monotonously,

the radius of curvature varies as a function of the distance to the optical axis according to an at least partly trigonometric function ([20], ([30]) in the external zone (Z3, Z4),

the radius of curvature varies linearly as a function of the distance to the optical axis in the outer zone (Z3, Z4).

the radius of curvature is substantially constant in the outer zone (Z3, Z4), the outer zone (Z3, Z4) comprises an intermediate zone (Z3) extending between the second distance (De / 2) and a third distance (2De-Pp / 2), and an end zone (Z4) s' extending between the third distance (De-Pp / 2) and the end of the lens, the third distance (2De-Pp / 2) being calculated from a mesopic pupil diameter (Pm) and a diameter of photopic pupil (Pp) of a patient,

the radius of curvature varies as a function of the distance to the optical axis according to an at least partly trigonometric function ([20], ([30]) in the intermediate zone (Z3),

the radius of curvature varies linearly as a function of the distance to the optical axis in the intermediate zone (Z3), and

the radius of curvature is substantially constant in the end zone (Z4).

It will be recalled that intraocular lenses are composed of a central part called "optical" of the implant used to correct the vision on a diameter of 6 to 6.5 mm, connected to a number of "haptics" used for centering and stability of the intraocular lens in the crystalline sac. Intraocular lenses can be monobloc, or with attached handles also called three-piece implant. The invention described above focuses on the "optical" part of the lens, and is therefore not restricted to a specific type of haptic. In general, the invention relates to a spherical, or spherocylindrical, intraocular lens for correcting associated astigmatism. It can be made in various types of hydrophilic, hydrophobic, liquid, etc. materials. As a variant, the variation of the asphericity Q could be obtained not by variation of the radius of curvature, but by variation of the index n of the material between its center and its periphery. In addition, other target Q values other than -1.00 such as -1, 05 or -1, 10, or others may also be obtained.

The invention also relates to a method of manufacturing an intraocular lens, in which a profile of radius of curvature is determined according to the method of calculating the radius of curvature profile described above, and in which an intraocular lens is manufactured according to this method. profile of radius of curvature. ANNEX A

Claims

1. Intraocular lens, characterized in that it has an optical axis (y), a central zone (ZI), and a peripheral zone (Z2, Z3, Z4) substantially symmetrical with respect to said optical axis (y) and s extending substantially perpendicularly thereto, said central zone (ZI) extending to a first distance (Pp / 2), and the peripheral zone (Z2, Z3, Z4) extending from the first distance (Pp) / 2) to the end of the intraocular lens, in which the central zone (ZI) has a nominal optical power, and the peripheral zone (Z2, Z3, Z4) has a continuously and monotonically varying radius of curvature as a function of the distance (x) to the optical axis (y), so that a target asphericity value is obtained at a second distance (De) from the optical axis (y), the first distance (Pp / 2) and the second distance (De) being calculated from a pupil diameter respectively photopic (Pp) and a mesopic pupil diameter (Pm) of a patient.

The intraocular lens according to claim 1, wherein the peripheral zone (Z2, Z3, Z4) comprises an emmetropia zone (Z2) extending between the first distance (Pp / 2) and the second distance (De). in which the radius of curvature varies continuously and strictly monotonically in the emmetropia zone (Z2).

3. The intraocular lens according to claim 2, wherein the radius of curvature varies as a function of the distance to the optical axis according to an at least partly trigonometric function ([20]) in the emmetropia zone (Z2).

The intraocular lens of claim 2, wherein the radius of curvature varies linearly as a function of distance to the optical axis in the emmetropia zone (Z2).

5. Intraocular lens according to one of the preceding claims, wherein the peripheral zone (Z2, Z3, Z4) comprises an outer zone (Z3, Z4), extending beyond the second distance (De), in which the radius of curvature varies continuously and monotonously.

Intraocular lens according to claim 5, wherein the radius of curvature varies as a function of the distance to the optical axis according to an at least partly trigonometric function ([20], ([30]) in the outer zone ( Z3, Z4).

Intraocular lens according to claim 5, wherein the radius of curvature varies linearly as a function of the distance to the optical axis in the outer zone (Z3, Z4).

The intraocular lens of claim 5, wherein the radius of curvature is substantially constant in the outer zone (Z3, Z4).

9. Intraocular lens according to one of the preceding claims, wherein the outer zone (Z3, Z4) comprises an intermediate zone (Z3) extending between the second distance (De / 2) and a third distance (2De-Pp / 2), and an end zone (Z4) extending between the third distance (De-Pp / 2) and the end of the lens, the third distance (2De-Pp / 2) being calculated from a mesopic pupil diameter (Pm) and a photopic pupil diameter (Pp) of a patient.

Intraocular lens according to claim 9, wherein the radius of curvature varies as a function of the distance to the optical axis according to an at least partly trigonometric function ([20], ([30]) in the intermediate zone ( Z3).

An intraocular lens according to claim 9, wherein the radius of curvature varies linearly as a function of the distance to the optical axis in the intermediate zone (Z3).

12. Intraocular lens according to one of claims 9 to 11, wherein the radius of curvature is substantially constant in the end zone (Z4).

13. A method of calculating a radius of curvature profile for an intraocular lens, characterized in that it comprises the following steps: a) receiving biometric parameters of a patient comprising at least a first radius of curvature (Rc), a photopic pupil diameter (Pp), and a mesopic pupil diameter (Pm)

b) determining an emmetropic distance (De) from at least the mesopic pupil diameter (Pm), and a second radius of curvature (Rp) from the first radius of curvature (Rc) and a value of target asphericity, c) calculating a radius of curvature profile in a direction substantially perpendicular to a desired optical axis (y) for the intraocular lens, wherein the radius of curvature is equal to the first radius of curvature (Rc) in a central area (ZI) extending between the optical axis (y) and a first distance (Pp / 2) calculated from at least the photopic pupil diameter (Pp), and wherein, in a peripheral zone (Z2, Z3, Z4) extending from the first distance (Pp / 2) to the end of the intraocular lens, the radius of curvature varies continuously and monotonically as a function of the distance (x) to the optical axis ( y), so that the radius of curvature is equal to the second radius of curvature (Rp) at the distance emmetropia (De) with respect to the optical axis (y).

A method of manufacturing an intraocular lens, wherein a radius of curvature profile is determined according to the method of claim 13, and wherein an intraocular lens is fabricated according to this radius of curvature profile.