Intraocular lenses with extended depth of focus

Abstract

The present invention relates to an intraocular lens (1) having an extended depth of focus, the intraocular lens (1) comprising an aspherical anterior optical surface and a posterior optical surface (2, 3).

Description

Technical Field

[0001] This invention relates to an intraocular lens (IOL). More specifically, this invention relates to an intraocular lens having extended depth of focus (EDOF). Background Technology

[0002] Age-related changes in proteins within the eye's natural lens can lead to cataract formation. In cataract surgery, an IOL (intraocular lens) is typically used instead of the natural lens.

[0003] By selecting an appropriate IOL focal length that is typically suited for long distances, the implantation of a monofocal IOL usually provides good quality vision.

[0004] However, an eye with an implanted IOL loses its residual accommodative capacity. Therefore, patients with monofocal IOLs typically need to wear near and intermediate glasses for activities requiring finer vision. This refers to a wide range of activities that can significantly impact a patient's daily life, such as reading and computer work.

[0005] Nowadays, patients increasingly hope to avoid wearing glasses after cataract surgery. To compensate for the shortcomings of monofocal IOLs, multifocal IOLs are being used more and more widely.

[0006] However, multifocal IOLs typically have a limited number of two or three focal points, while providing poor visual quality outside the focal length. In the case of a bifocal IOL, for example, designed with two focal points for near and two for far distances respectively, this can lead to difficulties in intermediate vision, thus requiring the patient to wear glasses. Another disadvantage of diffractive multifocal IOLs in certain cases is related to a certain percentage (approximately 18%) of incident light loss at high diffraction orders, which produces focal points outside the visually useful range. Furthermore, multifocal IOLs also have other undesirable side effects such as scattered light, halos, and glare. Summary of the Invention

[0007] The purpose of this invention is to provide an intraocular lens that provides better quality vision at both long and intermediate distances while minimizing the aforementioned side effects.

[0008] Therefore, the present invention provides an intraocular lens, the intraocular lens comprising:

[0009] - (single) front optical surface, and

[0010] - (Single) rear optical surface,

[0011] Both extend about the optical axis and are substantially radially outward relative to the optical axis;

[0012] Its features are:

[0013] -The first surface in the front optical surface and the rear optical surface is defined by the following equation:

[0014]

[0015] in:

[0016] ·Z st (r) is the component of the displacement vector measured along the optical axis from the vertex of the first surface to any point on the first surface, which is a radius r (considered a radial variable) away from the optical axis.

[0017] ·R st (∈R\{0}) is the radius of curvature of the first surface evaluated at its vertex;

[0018] ·κ st (R st ) is the quadratic curve constant of the first surface evaluated at its vertex, and is defined by the radius of curvature R of the first surface according to the following relationship. st Functions:

[0019]

[0020] Where erf represents the Gaussian error function, and a, b, c, A, B, C, and D are constant real numbers such that:

[0021] a∈[0.050; 0.075], b∈[-1; 0], c∈[-20; 0], A∈[-41; -39],

[0022] B∈[0.07; 0.13], C∈[-2.6; -2.0], and D∈[0.75; 1.25]

[0023] (For each i≥2) (∈R) are the 2i-th order aspherical coefficients of the first surface;

[0024] -The second surface in the front optical surface and the rear optical surface is defined by the following equation:

[0025]

[0026] in:

[0027] ·Z nd (r) is a component of the displacement vector measured along the optical axis (Z) from the vertex of the second surface to any point on the second surface, which is a radius r (considered a radial variable) away from the optical axis.

[0028] ·Rnd <0 is the radius of curvature of the second surface evaluated at its vertex;

[0029] ·κ nd (R nd ) is the quadratic curve constant of the second surface evaluated at its vertex, and is defined by the radius of curvature R of the second surface according to the following relationship. nd Functions:

[0030]

[0031] Where f, g, and h are constant real numbers such that:

[0032] f∈[0.08; 0.12], g∈[1.0; 1.6], h∈[0; 9],

[0033] (For each i≥2) (∈R) are the 2i-th order aspherical coefficients of the second surface;

[0034] The anterior and posterior optical surfaces (or equivalently, the first and second surfaces) enable the intraocular lens to provide an extended depth of focus.

[0035] The intraocular lens (IOL) according to the invention presents better quality vision at far and intermediate distances (e.g., compared to a bifocal IOL with two focal points for far and near distances), while minimizing side effects such as scattered light, halo and glare, and providing better quality vision at far distances (e.g., compared to a standard monofocal IOL).

[0036] In fact, the IOL includes an optical element (or central optical component) comprising a front surface (the so-called front optical surface) and a rear surface (the so-called rear optical surface) described by equations of the same form. Those skilled in the art will know that such equations define aspherical surfaces (as stated in the detailed embodiments, and in view of the following description)... Figure 4 Therefore, both the front and rear optical surfaces are aspherical, resulting in an optics device with a fully aspherical design that produces more negative spherical aberration compared to a standard monofocal IOL, and allows for an extension of the depth of focus (i.e., providing a single elongated focal point to enhance the "field of view") contributed by the surface equation parameters. This is based on the following description... Figure 6A -C、 Figure 7 , Figure 8 , Figure 9A -C (These figures present the results of experimental measurements), further comments and explanations are provided in the specific implementation.

[0037] The IOL according to the invention can be considered a monofocal IOL because it elongates a single focal point (for a monofocal IOL) to increase depth of focus (or visual range). It is not conceived as a multifocal IOL with a regular power map between focal points, nor as a multi-zone power IOL. This is obvious because most monofocal IOLs only correct vision to help cataract patients see things at (far) distances and therefore cannot improve intermediate vision required for many important daily tasks. In contrast, this monofocal IOL (with an elongated focal point) provides improved quality intermediate vision as well as good (far) distance vision, a significant advancement that makes it easier for patients to move around in daily life.

[0038] The IOL according to the invention advantageously provides extended depth of focus (EDOF) while minimizing the impact on peak (i.e., optimal focus) resolution, providing clear vision at mid-range distances, and minimizing common side effects of multifocal IOLs, such as scattered light, halo, and glare. In fact, refractive multifocal IOLs typically comprise multi-region optics (then a front and rear optical surface) divided into multiple sections (with surface geometries possibly described by different equations), which can lead to diffraction problems, such as halo, due to abrupt changes in geometry and / or optical power between these sections. In contrast, the IOL of the present invention comprises a single continuous and regular (or in other words, at least differentiable or smooth) front optical surface and a single continuous and regular rear surface, each surface being aspherical and described by a single smooth equation, which prevents such halo. Those skilled in the art will clearly understand that (typically) whether an IOL optical surface satisfies such an equation can be checked by simple profile comparison or overlay, or, if more in-depth analysis is required, by obtaining measurements of points on the cross-sectional curve of the IOL surface and comparing these measurements with the equation used to determine the IOL optical surface equation. IOL optical properties, such as EDOF or other properties described in the specific embodiments, can also be applied for comparison.

[0039] The IOL according to the invention is preferably refractive, more preferably purely refractive. More particularly, the properties optically provided by the front and rear surfaces are preferably refractive. However, IOLs including any diffraction features (e.g., components, portions of optical surfaces, etc.) are not excluded from the scope of the invention.

[0040] Another important aspect of this invention is that the claimed EDOF depends in a limited manner on (or, in other words, relatively independently of) the following:

[0041] -IOL's optical power

[0042] - Aperture (i.e., the opening through which light passes; for example, the diameter of the pupil of the eye when the IOL is used normally in an aphakic eye), and

[0043] - Spherical aberration of the cornea (e.g., spherical aberration of a corneal model, or spherical aberration of the cornea of ​​the eye when an IOL is used normally in an aphakic eye).

[0044] Based on the following description Figure 6A -B and Figure 7 This will be further explained in the specific embodiments. However, good control of EDOF, aperture, and corneal spherical aberration dependent on IOL power can also be understood from the aspherical equations defining the front and rear optical surfaces. In fact, it is known to those skilled in the art that the power derived from an optical surface generally depends on the refractive index associated with the raw materials constituting that surface and the geometry of that surface. The geometry of the surface is determined by the radius of curvature (at least for small orders r) and (optionally) by the quadratic constant of the optical surface evaluated at its apex. In this document, it is a reasonable assumption that the refractive index and the contribution of each of the front and rear optical surfaces to the overall IOL power are known. Furthermore, each of the quadratic constants of the front and rear optical surfaces is defined as a function of the radius of curvature of that surface by a novel, specific, and very advantageous smooth relation. Thus, at least for small orders, for each IOL power, each of the front and rear optical surfaces is characterized by its radius of curvature. Since all the relationships between these parameters and the optical power of the IOL are regular, the variations in the geometry of the front and rear optical surfaces relative to the optical power of the IOL are predetermined and regular. This allows for (at least locally) very favorable controlled and regular variations in the EDOF relative to the optical power, aperture, and corneal spherical aberration of the IOL.

[0045] The directly or indirectly controlled regular variations of the parameters in the equations for the front and rear optical surfaces, relative to the optical power of the IOL, are crucial for achieving this technical effect. In particular, it must be emphasized that this invention proposes a global optimization of the equation parameters by considering the goal of limited EDOF dependence. While it would be simpler to avoid performing any individual optimization of each parameter for each IOL optical power, this approach would also result in a high EDOF dependence on the IOL optical power.

[0046] Furthermore, and advantageously, the present invention also considers the modulation transfer function (MTF) associated with the IOL (i.e., an optical stage measurement used to evaluate lens performance, roughly a function of image resolution; more specifically, this function is known to those skilled in the art, and specifies how much contrast is captured as a function of spatial frequency). Generally, the MTF at the optimal focal point (i.e., at far distance) is inversely proportional to the EDOF, making it difficult to simultaneously obtain the dependence of the MTF on optical power, spherical aberration of the model cornea equipped with an optical stage, and aperture EDOF. However, in the case of the present invention, the equation parameters for the anterior and posterior optical surfaces are defined in such a way that this limitation is obtained. Based on the description below... Figure 6C and Figure 8 This is illustrated in the specific implementation. The range of constant real numbers is chosen around the specific preferred values ​​detailed below. For the optical power under consideration (optical power depends on the radius of curvature of the optical surface), these values ​​represent a regular and good trade-off between providing optimized EDOF or optimized MTF, in the sense that for optical surfaces made from average (ordinary) biomaterials with an average refractive index (e.g., about 1.52), these values ​​optimize both EDOF and MTF. It is relevant to consider the aforementioned range, which includes such practical uncertainties, in order to account for variations in these values ​​that may arise due to the choice of biomaterials and / or the IOL manufacturing process.

[0047] Another advantage of this invention is that, based on the use of current manufacturing techniques, these relationships between EDOF, IOL power, and equation parameters make it easier to design IOLs with different power values, as it can be achieved by utilizing the equations and relationships κ. st (R st ) and κ nd (R nd It is constructed in this way. More generally, it can be pointed out that these new relations, which express the quadratic curve constant of the surface of the IOL according to the invention as a function of the curvature radii of the preceding and subsequent optical surfaces, advantageously open up a technical perspective for the design and / or manufacture of IOLs (especially monofocal IOLs including optical surfaces whose quadratic curve constant is expressed by one of these relations as a function of their curvature radii).

[0048] Within the framework of this document, the “optical axis” of the eye is preferably a vector passing through the eye from one side to the other, pointing from its anterior segment to its posterior segment, the anterior segment comprising, in turn, the cornea, iris, and (natural or protected artificial) lens, and the posterior segment particularly comprising the retina. For an IOL according to the invention at an implantation site in the eye, the optical axis of the eye points from the anterior surface to the posterior surface and preferably corresponds to an optical axis intrinsically defined relative to the IOL. In particular, the term optical axis is currently and preferably used herein as a reference axis relative to the eye and / or the IOL.

[0049] Within the framework of this document, the “anterior” (or, respectively, “posterior”) side and / or surface of a portion of the eye or IOL, relative to a vector defined by an optical axis, is preferably located on the upstream (or, respectively, downstream) side and / or surface of that portion of the eye or IOL. For example, in the eye, the iris is located anteriorly relative to the (natural crystalline or claimed artificial) lens; the posterior surface of the iris is therefore the portion of the iris closest to the lens. Similarly, when a first portion of the eye or IOL is above (or, respectively, behind) a second portion of the eye or IOL, the first portion is located anteriorly (or, respectively, behind) relative to the second portion. Similarly, when an optical surface appears concave (or convex, respectively) when viewed in the same direction and with the same orientation as the vector defined by the optical axis (i.e., following the propagation of light), it is referred to as "anterior concavity (or posterior concavity)"; when an optical surface appears concave (or convex, respectively) when viewed in the same direction and with the opposite orientation to the vector defined by the optical axis, it is referred to as "posterior concavity (or convex, respectively)". The above concepts of anterior (anteriority), posterior (posteriority), or even the optical axis relative to the portion of the eye and / or IOL are known to those skilled in the art.

[0050] Within the framework of this invention, the first surface and the second surface are always different. Preferably, throughout the entire document, the first surface is the front optical surface and the second surface is the rear optical surface. However, the IOL surface can be flipped within the framework of this invention while retaining the main advantageous optical properties detailed above. For ease of reading, within the framework of this document, when specifically referring to parameters of the front or rear optical surface, the indicator symbols st and nd for equation parameters are replaced by the indicator symbols ant and post. For example, R ant and R post These correspond to the radii of curvature of the front and rear optical surfaces, respectively (evaluated at their respective vertices). When the first and second surfaces are considered the front and rear optical surfaces, respectively, within the framework of this document, the indicators st and nd are also replaced by the indicators ant and post, respectively.

[0051] Within the framework of this invention, as is generally known to those skilled in the art, the “vertices” of an optical surface (e.g., a front optical surface or a rear optical surface) are preferably defined as the intersection of the optical surface with an optical axis.

[0052] Within the framework of this invention, the "radius of curvature" of an aspherical surface (e.g., a front optical surface or a rear optical surface) evaluated at its apex is the distance between said apex and the center of curvature of the surface at that apex. The conventional notation for this radius of curvature is preferably defined as the sign of the displacement (vector) component measured along the optical axis from said apex to said center of curvature. Thus, if and only if the radius of curvature evaluated at its apex is negative (respectively, positive), the front optical surface is concave forward (respectively, convex forward) at its apex, and if and only if the radius of curvature evaluated at its apex is positive (respectively, negative), the rear optical surface is concave backward (respectively, convex backward) at its apex. In particular, for the IOL according to the invention, when R... nd When <0, the second surface of IOL is convex at its vertex and concave at its apex and around the vertex.

[0053] According to the terminology of those skilled in the art, if R ant >0 and R post <0, meaning that if and only if the current optical surface is forward-convex and if the rear optical surface is backward-convex, then the IOL according to the invention is called "biconvex". According to the terminology of those skilled in the art, if R ant <0 and R post <0, meaning that if the front optical surface is concave and the rear optical surface is convex, then the IOL according to the invention is referred to as "concave-convex". These terms, as used by those skilled in the art, describe the appearance of the IOL, with the front optical surface seen from the front and the rear optical surface seen from the back.

[0054] Within the framework of this invention, when a portion of the IOL preferably extends along a vector perpendicular to the optical axis, it is referred to as "radially outward" extension, pointing from a point shared with the optical axis to a point on a circle centered at that shared point. Similarly, when a portion of the IOL preferably extends along an arc of at least one circle on a plane perpendicular to the optical axis (centered at the intersection of the plane and the optical axis), it is referred to as "circumferential" extension.

[0055] Those skilled in the art will know that the adjective "distal" refers to the part of the body furthest from a reference organ or torso, while the adjective "proximal" refers to the other part of the body closest to a reference organ or torso. Within the framework of this document, these two definitions will preferentially apply to the parts of the eye and / or IOL according to the invention regarding distances relative to a reference optical axis.

[0056] Within the framework of this invention, the term "medium distance" preferably refers to an arm's length distance, such as when working on a computer or watching a car speedometer. More preferably, the term refers to a distance between 0.2 meters and 1.6 meters, and even more preferably, between 0.4 meters and 1.0 meters.

[0057] Within the framework of this invention, recall the meanings of some commonly used mathematical expressions:

[0058] • "<0" means "negative", that is, strictly less than 0;

[0059] • ">0" means "positive", that is, strictly greater than 0;

[0060] • “≤0” means “non-positive”, that is, less than or equal to 0;

[0061] • “≥0” means “non-negative”, that is, greater than or equal to 0;

[0062] • “∈” means “belongs to”;

[0063] • The set of real numbers in R;

[0064] • “R\{0}” refers to the set of non-zero real numbers;

[0065] • For γ∈R and δ∈R such that γ<δ, “[γ,δ]” refers to a closed interval of numbers between γ and δ, which contains γ and δ.

[0066] Furthermore, it is also well known that Einstein's summation convention is as follows:

[0067] ∑ i≥2 α 2i r 2i =α4r 4 +α6r 6 +α8r 8 +α 10 r 10 +...,

[0068] The indicator symbol "i" here is an integer greater than or equal to 2.

[0069] Within the framework of this document, the “Gaussian error function” denoted by erf refers to the well-known, invertible, sigmoid special function defined in real numbers by the following formula (in particular).

[0070]

[0071] Within the framework of this invention, the term "regular" for a function or surface preferably refers to a function or surface that is at least differentiable (or smooth). Within the framework of this invention, the terms "function of," "dependent on," and similar terms should not be interpreted restrictively as having limited dependence on a specified parameter unless such limitation is explicitly stated.

[0072] Within the framework of this document, an element is introduced using the indefinite article “a,” “one,” or the definite article “the,” but this does not preclude the existence of multiple such elements. In this document, the terms “first,” “second,” “third,” etc., are used only to distinguish elements and do not imply any order among these elements.

[0073] Within the framework of this document, the use of the verbs “contain,” “include,” “involves,” or any other variants, and their inflectional forms, cannot in any way exclude the presence of elements other than those mentioned.

[0074] According to a preferred embodiment of the invention, the IOL has an optical power between 10D and 35D. Optionally, it differs from 13.5D and / or 14D.

[0075] Within the framework of this document, the “optical power” of the IOL is preferably the average optical power measured without correction within a (reading) window centered on an optical axis with a diameter of 3 mm.

[0076] According to a preferred embodiment of the present invention, in relation κ st (R st ) and κ nd (R nd The constant real number involved in the definition of ) lies in the following restricted range of values:

[0077] a∈[0.060; 0.075] and / or b∈[-0.5; -0.2] and / or c∈[-12; -10]

[0078] And / or A∈[-40.1; -39.9] and / or B∈[0.080; 0.095] and / or C∈[-2.35; -2.05] and / or D∈[0.90; 1.1]

[0079] And / or f∈[0.085; 0.105] and / or g∈[1.05; 1.40] and / or h∈[3; 6].

[0080] These intervals can be considered individually or in combination. For example, the first part of these constant real numbers can be considered within a wider interval of the

[0008] segment, while the second part of these constant real numbers can be considered within these restricted intervals. Alternatively, these restricted intervals can be considered in combination, and all terms "and / or" preferably mean "and". Alternatively, these constant real numbers may lie in an interval of values ​​smaller than the interval of the

[0008] segment, thus:

[0081] a∈[0.055; 0.070] and / or b∈[-0.7; -0.2] and / or c∈[-15; -5]

[0082] And / or A∈[-40.5; -39.5] and / or B∈[0.08; 0.10] and / or C∈[-2.4; -2.2] and / or D∈[0.85; 1.15]

[0083] And / or f∈[0.09; 0.11] and / or g∈[1.20; 1.45] and / or h∈[3; 7].

[0084] These intervals can be considered individually or in combination. For example, the first part of these constant real numbers can be considered within a wider interval of the

[0008] segment, the second part of these constant real numbers can be considered within the aforementioned restricted interval, and the third part of these constant real numbers can be considered within these other smaller intervals. Optionally, these other smaller intervals can be considered in combination, and all terms "and / or" are preferably "and". These constant real numbers lie within smaller intervals of values ​​such that:

[0085] a∈[0.060; 0.065] and / or b∈[-0.5; -0.3] and / or c∈[-12; -10]

[0086] And / or A∈[-40.1; -39.9] and / or B∈[0.090; 0.095] and / or C∈[-2.35; -2.25] and / or D∈[0.9; 1.1]

[0087] And / or f∈[0.095; 0.105] and / or g∈[1.25; 1.40] and / or h∈[4; 6].

[0088] These intervals can be considered individually or in combination. For example, the first part of these constant real numbers can be considered within a wider interval of the

[0008] segment, the second part of these constant real numbers can be considered within the aforementioned restricted interval, the third part of these constant real numbers can be considered within the aforementioned other smaller intervals, and the fourth part of these constant real numbers can be considered within these further smaller intervals. Very optionally, these intervals are considered in combination, and all terms “and / or” preferably mean “and”. As mentioned above, the selection of intervals corresponds to uncertainties, such as uncertainties in the selection of biological raw materials and / or the manufacturing process of the intraocular lens. Such uncertainties can cause slight variations in the selection of the radius of curvature or curve constants used to optimize the EDOF and MTF of the IOL (at a given IOL power).

[0089] The exact value of each of these constant real numbers may optionally be given as:

[0090] a = 0.0621 and / or b = -0.396 and / or c = -11.035

[0091] And / or A = -40 and / or B = 0.092 and / or C = -2.29 and / or D = 1

[0092] And / or f = 0.0989 and / or g = 1.277 and / or h = 4.663.

[0093] Each of these values ​​can be considered individually or in combination with one or more other values, and all terms “and / or” preferably mean “and”. The range of constant real values ​​mentioned above is around these specific values. It must be noted that these values ​​can be obtained by interpolation and / or approximation curves of specific real values ​​chosen for the radius of curvature and conic constant of the aspherical equations defining the front and rear optical surfaces. In particular, although such precise value selection provides the IOL according to the invention, variations around these precise values ​​are entirely within the scope of the invention. Based on the description below... Figure 5A -C, further explanation is provided in the specific implementation. This is why the "envelops" are considered to revolve around two relations κ defined by the choice of precise values. st (R st ) and κ nα (R nd The margin of uncertainty in the graph is meaningful. According to the invention, these envelopes are considered in the form of the aforementioned intervals, but other types of envelopes can also be defined. In particular, according to a preferred embodiment of the invention:

[0094]

[0095]

[0096]

[0097] (Note the relation marked with ★) where, for each j∈{1, 2, 3}, p j It's a number, p j ≥10, and optionally, p j =10, or alternatively, p j =20, more optionally p j =50. Those skilled in the art will understand that, taking into account all the precise values ​​described above, these relations represent true quadratic curve constants of the first and second surfaces that are "sufficiently close" to those derived from relation κ. st (R st ) and κ nd (R nd The curve constant is defined as 1 / p. To understand "close enough," the absolute value of the relevant relative deviation must be understood. j The boundary is defined by choosing an exact value for the two relations κ. st (R st And, deviation 1 / p j It also allows for the evaluation of the interpolated and / or approximate values, and then the deviation 1 / p. j This can vary depending on the latter. As a non-limiting illustrative example, for the exact values ​​mentioned above, one could consider p1 = 10, p2 = 15, p... j =20. These deviations also define another such envelope in conjunction with the aforementioned intervals. Alternatively, these envelopes can be considered alone, instead of the intervals comprising the

[0008] segment containing constant real numbers, thereby defining alternative inventions within the same framework of the invention. In this case, the relation (★) can be summarized as follows:

[0098]

[0099]

[0100]

[0101] Where a, b, c, A, B, C, D, f, g, h can be any value explicitly disclosed in this document, especially the values ​​in sections

[0034] -

[0036] and

[0070] -

[0073] , and where for each j∈{1, 2, 3}, p j It is a number greater than or equal to 10, and optionally, p j =10, or alternatively, p j =20, more optionally pj =50.

[0102] For the specific selection of the radii of curvature and curve constants of the front and rear optical surfaces, other precise values ​​can be considered more accurate. As an example, for an IOL with an optical power less than or equal to 27.5D, constant real numbers f, g, and h are more preferably given precisely by the following equations: f = 0.1032 and / or g = 1.372 and / or h = 5.1353. More preferably, these values ​​are considered in combination, and the term "and / or" preferably means "and". This will be based on... Figure 5C Specific explanation. As another example, the aforementioned values ​​B = 0.092 and / or C = -2.29 can be replaced with B = 0.081 and / or C = -2.095 (or, optionally, also B = 0.085 and / or C = -2.168), thereby providing another approximate curve for the selection of specific values ​​for the radius of curvature and quadratic constant of the aspherical equations defining the front and rear optical surfaces, to smoothly achieve the desired optimized EDOF and MTF relative to the primary selection of at least IOL optical power. In particular, according to the independent corresponding embodiment of the invention, the relation...

[0103]

[0104] and / or

[0105]

[0106] and / or

[0107]

[0108] If the optical power of the IOL is strictly greater than 27.5D; and / or

[0109]

[0110] If the optical power of the IOL is less than or equal to 27.5D;

[0111] For each j∈{1, 2, 3, 4}, it is preferable to satisfy p j '≥10, preferably p4'>P3'. All or part of these last relations can be considered in combination and / or by replacing all or part of the relevant relations (★).

[0112] According to a first preferred embodiment of the present invention, the IOL has an optical power strictly less than 14D, and R st <0. Specifically, the first surface is concave at its apex and convex at its apex. According to a second preferred embodiment of the invention, the IOL has an optical power greater than or equal to 14D, and R st>0. Specifically, the first surface is convex in front and concave in back at its apex. In other words, combining these two preferred embodiments, preferably, if and only if R st When <0, the optical power of IOL is strictly less than 14D.

[0113] Preferably, according to any of these preferred embodiments, the radius of curvature R of the first surface st It continuously and regularly depends on the optical power (depending on the aforementioned considered range defined by the optical power). Preferably, and independently of these preferred embodiments, the radius of curvature R of the second surface... nd The optical power is continuously and regularly dependent on the intraocular lens. The continuity and regularity of the variation of the radius of curvature of each optical surface is a natural and preferred choice for achieving the desired technical effect of this invention. It also implies the regularity of the variation of the quadratic curve constant of each optical surface, since it is expressed regularly as a function of the relevant radius of curvature.

[0114] Within the framework of this invention, at least one of the aspherical coefficients in at least one of the front optical surface equation and the rear optical surface equation (preferably both optical surface equations) is non-zero. IOL optics employ an aspherical design, which allows for an extended depth of focus due to the contribution of these non-zero aspherical coefficients. According to a preferred embodiment of the invention, the aspherical coefficients of the front optical surface and / or the rear optical surface, less than or equal to order 10, are non-zero. The contribution of all these non-zero aspherical coefficients makes very high EDOF performance attainable. Specifically, it introduces a fully aspherical geometry to the front optical surface and / or the rear optical surface, which includes a loop at the inflection point (i.e., the inflection point) of curvature at the intermediate optical diameter. Preferably, the absolute values ​​of the aspherical coefficients decrease with respect to their order and / or are bounded by 0.1. More preferably, they follow the following relationship:

[0115]

[0116] And / or, preferably and,

[0117]

[0118] These aspherical coefficients correspond to the general form of sideperturbation of the aspherical surface around its vertices. Preferably, the aspherical coefficients of orders greater than 10 for the front and / or rear optical surfaces are negligible and / or approximately zero and / or equal to zero. In other words, they are essentially zero, and preferably zero.

[0119] Preferably, the aspheric coefficients of the anterior and / or posterior optical surfaces are continuously and regularly dependent on the optical power of the intraocular lens (IOL). Specifically, preferably, all parameters (radius of curvature, quadratic constant, and aspheric coefficient) defining the anterior and / or posterior optical surfaces are regularly dependent on the optical power of the IOL.

[0120] As a specific embodiment of the present invention, precise equations are now provided for selecting the front and rear optical (aspherical) surfaces of an IOL with a predetermined optical power:

[0121] According to a first specific embodiment of the present invention, the optical power of the IOL is 15D, and

[0122] R ant =79.63mm and / or κ ant (R ant = -80.00 and / or

[0123] and / or and / or

[0124] and / or and / or

[0125] R post = -13.82mm and / or κ post (R post ) = 5.95 and / or

[0126] and / or and / or

[0127] and / or

[0128] According to a second specific embodiment of the present invention, the optical power of the IOL is 20D, and

[0129] R ant =21.60mm and / or κ ant (R ant ) = -25.61 and / or

[0130] and / or and / or

[0131] and / or and / or

[0132] R post = -15.21mm and / or κ post (R post = 8.10 and / or

[0133] and / or and / or

[0134] Such as / or

[0135] According to a third specific embodiment of the present invention, the optical power of the IOL is 25D, and

[0136] R ant =11.47mm and / or κ ant (R ant ) = -3.67 and / or

[0137] and / or and / or

[0138] and / or and / or

[0139] R post = -19.47mm and / or κ post (R post ) = 17.61 and / or

[0140] Such as / or and / or

[0141] and / or

[0142] For each of the aforementioned optical powers, these specific data are preferably considered in combination. Within the framework of this document, for IOLs in a dry state, any specific data mentioned as geometric parameters of the front and rear optical surfaces are given. Considering that factors such as the biological raw materials constituting the IOL and / or manufacturing processes and conditions can affect these values, these values ​​are appreciated relative to an uncertainty of up to 10%, more preferably 5%, in absolute value. As an example, the radii of curvature of these first, second, and third embodiments can be replaced by other preferred values, such as:

[0143] -R ant = 86.11mm, and / or R post = -14.00mm; and / or

[0144] -R ant =22.01mm, and / or R ppst = -15.42mm; and / or

[0145] -Rant =11.61mm, and / or R post = -19.88mm.

[0146] Without changing the values ​​of other equation parameters.

[0147] The apparent geometry of the front and rear optical surfaces will now be described. Preferably, according to an embodiment of the invention with an IOL power greater than or equal to 14D:

[0148] - Using the plane perpendicular to the optical axis as the zero-elevation reference plane, and the optical axis as the reference axis for elevation evaluation, the elevation diagram on the radial coordinates of the front optical surface is as follows:

[0149] • A local minimum is observed at the apex of the front optical surface.

[0150] • Increasing from the vertex of the former optical surface to the edge of the surface;

[0151] -Using a plane perpendicular to the optical axis as the zero-elevation reference plane, and the optical axis as the reference axis for elevation evaluation, the elevation map evaluated on the radial coordinates of the rear optical surface is presented as follows:

[0152] • Local maximum at the vertex of the rear optical surface

[0153] • The local minimum value at a positive distance from the edge of the rear optical surface.

[0154] • The inflection point located between the local maximum and the peripheral local minimum.

[0155] and:

[0156] • The local minimum value decreases from the vertex of the rear optical surface to the periphery.

[0157] • The value increases from the local minimum at the periphery to the edge of the subsequent optical surface.

[0158] Preferably, according to an embodiment of the present invention where the optical power of the IOL is strictly greater than 12D and strictly less than 14D:

[0159] -Using a plane perpendicular to the optical axis as the zero-elevation reference plane and the optical axis as the reference axis for elevation evaluation, the elevation map evaluated on the radial coordinates of the front optical surface is presented as follows:

[0160] • Local maximum at the vertex of the front optical surface

[0161] • The local minimum value at a positive distance from the edge of the front optical surface.

[0162] • The inflection point located between the local maximum and the peripheral local minimum.

[0163] and:

[0164] • The local minimum value decreases from the vertex of the former optical surface to the periphery.

[0165] • It increases from the peripheral local minimum to the edge of the front optical surface.

[0166] - Using a plane perpendicular to the optical axis as the zero-elevation reference plane, and the optical axis as the reference axis for elevation evaluation, an elevation map is evaluated on the radial coordinates of the rear optical surface.

[0167] • Local maximum at the vertex of the rear optical surface

[0168] • The local minimum value at a positive distance from the edge of the rear optical surface.

[0169] • The inflection point located between the local maximum and the peripheral local minimum.

[0170] and:

[0171] • The local minimum value decreases from the vertex of the rear optical surface to the periphery.

[0172] • The value increases from the local minimum at the periphery to the edge of the subsequent optical surface.

[0173] In particular, in this case, the two elevation maps of the front and rear optical surfaces have similar profiles.

[0174] Preferably, according to an embodiment of the present invention where the optical power of the IOL is less than or equal to 12D:

[0175] - Using a plane perpendicular to the optical axis as the zero-elevation reference plane and the optical axis as the reference axis for height evaluation, the elevation map is evaluated on the radial coordinates of the front optical surface:

[0176] • A local maximum is observed at the apex of the front optical surface.

[0177] • Decrease from the vertex of the former optical surface to the edge of the surface;

[0178] - Using a plane perpendicular to the optical axis as the zero-elevation reference plane and the optical axis as the reference axis for elevation evaluation, the elevation map is evaluated on the radial coordinates of the rear optical surface:

[0179] • A local maximum is observed at the apex of the rear optical surface.

[0180] • Decrease from the vertex of the rear optical surface to the edge of the surface.

[0181] In particular, in this case, the two elevation maps of the front and rear optical surfaces have similar profiles.

[0182] The geometric properties of the anterior and posterior optical surfaces described in the preceding three paragraphs are attributable to the asphericity of these surfaces, which is governed by equations for these surfaces (aspheric), particularly for the preferred embodiments of the invention where the aspheric coefficients of the anterior and posterior optical surfaces of order 10 or less are non-zero. These geometric properties provide high optical quality (described by high MFT) for the IOL and result in EDOF that depends only slightly on optical power, aperture, and corneal spherical aberration.

[0183] According to a preferred embodiment of the invention, the front and rear optical surfaces are cut from a hydrophobic biomaterial with a refractive index between 1.40 and 1.65. Preferably, the biomaterial is flare-free. Flares (also known as fluid-filled microvacuoles) can form within some IOL materials and develop in various shapes, sizes, and densities after IOL implantation. Some commercially available IOLs exhibit flares after implantation, which can affect visual quality. Preferably, the biomaterial contains a UV blocker (in the strictly less than 400 nm range) and / or a yellow chromophore to reduce the transmittance of potentially phototoxic light in the violet-blue range (between 400 nm and 500 nm). Preferably, the refractive index is equal to 1.52.

[0184] According to a preferred embodiment of the invention, the front optical surface and the rear optical surface are separated by an inner body of a predetermined central thickness, which is measured along the optical axis and is between 0.30 mm and 0.70 mm. Advantageously, this central thickness allows for the attachment of a flexible tactile portion to the periphery of the optics consisting of the inner body and the front and rear optical surfaces.

[0185] According to a preferred embodiment of the invention, both the front and rear optical surfaces have a diameter measured perpendicular to the optical axis, which is between 4.70 mm and 5.00 mm, preferably between 4.80 mm and 4.95 mm, and more preferably between 4.85 mm and 4.91 mm. This diameter is preferably suitable for so-called transparent optics. During the manufacturing process of the optics (or central optical components) of the IOL, the target value is approximately 5 mm. However, as described below, the junction between the tactile portion of the IOL and its optics must be optimized, which will result in a possible reduction in the size of the transparent optics, which is more typically about 4.85 mm after the IOL is manufactured. In particular, the geometry of the front and rear optical surfaces terminates at the edge of the IOL optics defined by the junction between the IOL optics and the tactile portion, referred to as the "edge of these optical surfaces".

[0186] According to embodiments of the invention, the optical refraction of the combination of the anterior and posterior optical surfaces with a corneal model (located anteriorly and externally to the IOL) provides a continuous and regular graph of optical power, including a central global maximum (refractive power) (which can be associated with closer distances, such as intermediate distance vision), said central global maximum along an optical axis surrounded by a spread central region of lower optical power (for farther distance vision, such as far distance). The term "lower" must be understood relative to the central global maximum (peak power). "Corneal model" is, for example, an "average corneal model," that is, a corneal model that provides 0.28 μm (±0.2 μm) of corneal spherical aberration to the average human eye in the IOL plane at a 5.15 mm aperture. The average corneal model is completely standard and well known to those skilled in the art. It is denoted by ISO 2. Preferably, the central region is "spread," that is, it extends over approximately half the diameter of the anterior and posterior optical surfaces. Preferably, the first ring of points (or inflection points, or local minimum values ​​of optical power) in the graph surrounds the central region. Optionally, the graph also includes a second ring of points that are local maximum values ​​of optical power, the second ring surrounding the first ring. The following describes... Figure 10A -B illustrates this regularity in the graph. This naturally produces the EDOF provided by the IOL. It is advantageous to indicate that the graph of optical power is regular. In particular, the IOL simultaneously provides patients with high optical quality for different distances without sudden changes in optical power along the optics that could easily cause side effects such as scattered light, halos, or glare.

[0187] According to a more preferred embodiment of the present invention, the intraocular lens according to the present invention comprises:

[0188] - Central optical components (or optical devices),

[0189] The front surface of the central optical component is the front optical surface, and

[0190] • The rear surface of this central optical component is the rear optical surface;

[0191] - Multiple flexible tactile parts connected to a central optical component and configured to stabilize an artificial lens within the capsular bag of an aphakic eye.

[0192] The term "center" refers to an extension of an optical element around and / or centered on an optical axis. Preferably, the term "center" does not refer to a portion of an IOL optics element, but rather to the entire optical component of the IOL optics element. Preferably, the first surface is the front optical surface.

[0193] Preferably, the IOL comprises four closed flexible tactile portions, each forming a ring based on a central optical element. Preferably, the thickness of the tactile portion, measured along the optical axis, is between 0.20 mm and 0.50 mm, more preferably equal to 0.34 mm. Preferably, the tactile portion is made of the same hydrophobic biomaterial as the central optical element. Preferably, the tactile portion is cut by a milling machine. Preferably, the plurality of flexible tactile portions are four closed flexible tactile portions, each forming a ring based on a central optical element. These four closed flexible tactile portions are preferably arranged symmetrically around the central optical element along the diagonal of a rectangle, providing four contact points such that the contact angle between the tactile portion and the surrounding ocular tissue is maximized when the IOL is used normally in an aphakic eye. Therefore, controlled compensation for changes in capsular size can be advantageously achieved through radial deformation of the tactile portion.

[0194] Preferably, the distance between the tip of the flexible tactile portion (front) and the main (or intermediate) optical plane of the central optics, measured along the optical axis, continuously and regularly depends on the optical power of the intraocular lens (IOL). It is advantageous and important to consider this distance and calculate it as a function of the IOL's optical power. Indeed, as mentioned above, the aspherical geometry of the anterior and posterior optical surfaces varies regularly according to the IOL's optical power. This means that the main optical plane is not constant, and its position varies as a function of the IOL's optical power. Therefore, it is important to adjust the connection between the tactile portion and the central optics at the junction of the tactile portion and the central optics, both in terms of its position parallel to the optical axis (which then results in an offset) and the angle between the main optical plane and the proximal portion of the tactile portion. This is as important as ensuring that the temples of the glasses fit the body properly. Advantageously, the present invention proposes to consider this through the aforementioned distance. Furthermore, it is also preferable to select the geometry and distance of the tactile portion to ensure IOL stability parallel to the optical axis when the IOL is implanted in the capsular bag of an aphakic eye. Preferably, it is bounded by 0.45 mm and increases continuously with increasing optical power. Based on the description below... Figure 12A -B, In the specific implementation, the distance as a function of the optical power of the IOL is further explained.

[0195] In other words, according to a preferred embodiment of the highly preferred embodiment of the present invention, the distance between the tip of the flexible tactile portion (front) and the main (or intermediate) optical plane of the central optical component, measured along the optical axis, corresponds to an image of the optical power of the intraocular lens via a continuous regular function, thereby continuously increasing with increasing optical power. This distance is bounded at 0.45 mm, such that when the intraocular lens is implanted in the capsular bag of an aphakic eye, the main optical plane is stably parallel to the optical axis (longitudinally). This distance and the associated advantages are part of the present invention. In particular, the present invention also provides an intraocular lens (IOL) comprising:

[0196] - Central optical component (or optical device), which includes:

[0197] • Aspherical front optical surface, and

[0198] • The rear optical surface of an aspherical surface;

[0199] - Multiple flexible tactile parts connected to the central optical component;

[0200] The distance between the top of the flexible tactile part and the main optical plane of the central optical component, measured along the optical axis, is continuously and regularly dependent on the optical power of the IOL. Any embodiment and / or advantage of the IOL described in the previously described paragraph

[0008] can be extended to other IOLs according to the invention.

[0201] According to a preferred embodiment of the invention, the IOL retains its shape after rotating 180° around the optical axis. This makes it easier to insert and manipulate the IOL in the eye, as its shape and, in particular, the form of the tactile portion naturally adjust to the possible position during rotation during surgery.

[0202] The present invention also provides a method for manufacturing an intraocular lens according to the present invention, comprising the following steps:

[0203] (a) Modeling optical devices with cross-sectional configurations of aspherical optical surfaces;

[0204] (b) Calculate the refractive efficiency distribution of light propagating through the modeled optical device;

[0205] (c) Select the profile parameters of the aspherical optical surface based on the calculated refractive efficiency distribution to obtain the desired refractive efficiency; and

[0206] (d) Forming biomaterials into modeled optical devices with selected parameters.

[0207] The manufacturing method according to the invention readily provides an IOL with optimized parameters for improving visual quality at long and mid-range distances. Preferably, the profile parameters of the aspherical optical surface selected in step (c) continuously and regularly depend on the optical power of the intraocular lens. For each surface, these parameters preferably include (more preferably) the radius of curvature and curve constant evaluated at the vertices of the surface, as well as the aspheric coefficient. Embodiments and advantages of the IOL according to the invention are adapted to the method according to the invention with necessary modifications. In particular, step (c) is preferably performed according to a parameter table comprising optimized profile parameters of the aspherical surface for the optical power of each desired IOL in relation to the desired refractive efficiency. According to a predetermined relationship κ... st (R st ) and κ nd (R nd These parameters are determined very easily. Preferably and particularly, in step (c), the quadratic curve constant κ of the first surface, evaluated at the vertex of the first surface among these aspherical optical surfaces, is selected. st The constant κ of the quadratic curve is obtained through the following relationship. st The radius of curvature R of the first surface evaluated at this vertex. st The function.

[0208]

[0209] Where erf represents the Gaussian error function, and a, b, c, A, B, C, and D are constant real numbers; and in step (c), the quadratic curve constant κ of the second surface is evaluated at the vertex of the second surface among these aspherical optical surfaces. nd κ nd The radius of curvature R of the second surface evaluated at this vertex is given by the following relationship. nd function

[0210]

[0211] Where f, g, and h are constant real numbers. All embodiments and advantages of the IOL according to the invention, with necessary modifications, are applied to the preferred embodiments of the manufacturing method according to the invention, relating to these relations and / or constant real numbers a, b, c, A, B, C, D, f, g, and h. As another independent preferred embodiment of the manufacturing method for the IOL described in paragraph

[0053] , the method includes the step of selecting a distance (HC) by a continuous and regular function, the distance (HC) being a function of the optical power of the intraocular lens (1) as an image of optical power, the distance (HC) being a distance measured along the optical axis between the principal optical plane of the flexible tactile portion and the central optical component, the distance continuously increasing with increasing optical power and bounded at 0.45 mm, so as to achieve desired longitudinal stability of the principal optical plane parallel to the optical axis when the intraocular lens is implanted into the capsular bag of the aphakic eye. Attached Figure Description

[0212] Other features and advantages of the present invention will become apparent from the following detailed description of the embodiments, in which reference is made to the accompanying drawings, wherein:

[0213] - Figure 1 A simplified planar representation of the front surface of an IOL according to a preferred embodiment of the present invention is shown.

[0214] - Figure 2 A simplified comparison is shown between light focusing through a monofocal lens and light focusing through an IOL according to the invention;

[0215] - Figures 3A-3D Cross-sectional views of the front and rear optical surfaces of an IOL according to a preferred embodiment of the present invention are shown.

[0216] - Figure 4 A schematic diagram of an aspherical surface is shown;

[0217] - Figure 5A The diagram shows a graphical representation of the quadratic curve constant of the first surface according to a preferred embodiment of the present invention when the radius of curvature is positive. The quadratic curve constant of the first surface is defined as a function of the radius of curvature of the first surface.

[0218] - Figure 5B The diagram shows a graphical representation of the quadratic curve constant of the first surface according to a preferred embodiment of the present invention when the radius of curvature is negative. The quadratic curve constant of the first surface is defined as a function of the radius of curvature of the first surface.

[0219] - Figure 5CA graphical representation of the curve constant of the second surface according to a preferred embodiment of the present invention is shown, the curve constant being defined as a function of the radius of curvature of the second surface;

[0220] - Figure 6A -C shows a graphical representation of the experimental (on an optical stage) and interpolation of the EDOF, spherical aberration, and MTF of an IOL according to a preferred embodiment of the present invention, wherein the EDOF, spherical aberration, and MTF of the IOL are functions of their nominal optical power;

[0221] - Figure 7 Graphical representations of the EDOF of an IOL of moderate refractive power according to a preferred embodiment of the present invention, in combination with aperture, are shown for three different models of corneal spherical aberration.

[0222] - Figure 8 Graphical representations of the MTF of an intermediate refractive IOL as a function of aperture for three different models of corneal spherical aberration are shown;

[0223] - Figures 9A-9C Graphical representations of (fourth-order) spherical aberration as a function of aperture are shown for a corneal model, an IOL according to a preferred embodiment of the present invention, and a combination of the two.

[0224] - Figure 10A -B shows a photometric diagram obtained by combining the front and rear optical surfaces with a corneal model according to an embodiment of the present invention;

[0225] - Figure 11A -C shows a simplified cross-sectional representation of the IOL according to a preferred embodiment of the present invention;

[0226] - Figure 12A The connection between the tactile part and the central optical component of an IOL according to an embodiment of the present invention is shown;

[0227] - Figure 12B A graphical representation of the distance measured along the optical axis between the top of the flexible tactile part and the main optical plane of the central optical component of the IOL according to a preferred embodiment of the present invention is shown, which is a function of the optical power of the IOL;

[0228] - Figure 13 A graphical representation of the defocus MTF measurements on an optical stage is shown for both a standard monofocal IOL and an IOL according to a preferred embodiment of the present invention.

[0229] The figures are not drawn to scale. Generally, similar elements in the figures are represented by similar reference numerals. Within the framework of this document, identical or similar elements may have the same reference numerals. Furthermore, the presence of reference numerals in the figures should not be considered limiting, including when such numerals appear in the claims.

[0230] Nevertheless, the graphical representations are illustrated in a way that exposes each value or a range of values ​​that can be derived from these graphical representations. Figure 5A -C、 Figure 6A -C、 Figure 7 , Figure 8 and Figure 9A -C is considered to be a number that accurately reproduces the measured values ​​and / or interpolated (or approximate) curves. Detailed Implementation

[0231] This section provides specific preferred embodiments of the invention. These embodiments are described with reference to the accompanying drawings, but the invention is not limited to these drawings. Specifically, the drawings or figures described below are merely illustrative and are not intended to be limiting in any way. This specific embodiment will only relate to preferred embodiments of the invention, wherein the first surface and the second surface are the front optical surface and the rear optical surface, respectively. Then, for ease of reading, the reference numerals st and nd are replaced by the reference numerals ant and post, respectively. Furthermore, reference numerals 2 (respectively, 3) in the specific embodiment and drawings are used to denote the front (respectively, rear) optical surface (which then corresponds to the first (in turn, the second) surface).

[0232] As shown in the figure below, the present invention provides a refractive intraocular lens (IOL) 1 with extended depth of focus (EDOF), comprising a single aspherical anterior optical surface 2 and a single aspherical rear optical surface 3, the anterior optical surface 2 and the rear optical surface 3 extending radially outward relative to an optical axis Z and rotationally symmetrical about the optical axis Z. The optical axis Z points from the anterior optical surface 2 to the rear optical surface 3, or in other words, from the overall anterior surface of the IOL 1 to the overall rear surface of the IOL 1. Reference numerals 21 and 31 denote the vertices of optical surfaces 2 and 3, respectively.

[0233] As described in the disclosure of this invention, each of optical surface 2 and optical surface 3 is defined by a single equation of the following form.

[0234]

[0235] For any aspherical surface, more typically denoted by S (e.g., front optical surface 2 or rear optical surface 3), which includes vertices more typically denoted by V, Figure 4This illustrates how such an aspherical surface can be defined by an equation of this form. The figure shows the approximate circle of the cross-section of the surface S (and then the curve) at vertex V, which includes the optical axis Z. Specifically, this circle approximates the cross-section of the surface S around vertex V. The center of curvature C of this circle lies on the optical axis Z. The radius of this circle corresponds to the so-called radius of curvature R of the cross-section of the surface S evaluated at vertex V. Figure 4 In the illustrated embodiment, it is assumed that the component of the displacement (vector) from vertex V to the center of curvature C (measured along the optical axis Z) is positive, and therefore the conventional sign of the radius of curvature R is positive. In fact, the direction and orientation of this displacement (vector) are the same as the optical axis Z. Those skilled in the art know that the quadratic constant κ of the cross section of surface S evaluated at vertex V defines the overall deviation of the cross section of surface S from the osculating circle (e.g., a hyperbola, parabola, or elliptic). Considering that the aspherical surface is at least locally, rotationally, symmetric about the optical axis Z in the vicinity of vertex V, these concepts of the radius of curvature R evaluated at vertex V and the quadratic constant κ are directly extended to surface S. Specifically, the radius of curvature R corresponds to the radius of the osculating sphere evaluated at vertex V. For each i ≥ 2, α 2i These are the real coefficients of order 2i (so-called aspherical coefficients) of surface S. These coefficients essentially correspond to the (lateral) variations of the surface defined by the radius of curvature R and the quadratic constant κ. Based on all these parameters R, κ, α4, α6, α8... the equation defines surface S by expressing the data z(r) as a function of the radial variable r, both of which are as follows... Figure 4 As shown. The data z(r) corresponds to the component of the displacement (vector) measured along the optical axis Z from the vertex V to any point on the surface, which is a radius r away from the optical axis Z. Equivalently, the data z(r) corresponds to the vector... The Z component is given by P, where P is any point on surface S at a distance r from the optical axis Z. Considering the local polar coordinates (r, z) on surface S, the data z(r) equivalently corresponds to the coordinates of a point on surface S along the optical axis Z, with the radial coordinate of that point being r (calculated starting from vertex V). Vertex V typically corresponds to the point (r = 0; z(r) = 0). Figure 4 In the illustrated embodiment, because the displacement (vector) points in the same direction and orientation as the optical axis z, the data z(r) is positive. In this case, surface S is convex (concave). Figure 4 A very general illustration of the above equations for aspherical surfaces. The exact forms of the claimed front optical surface 2 and rear optical surface 3, their concavity or convexity, and the symbol R for their radii of curvature. ant and R post , or the sign of their data z(r) is not restrictive.

[0236] like Figure 1 As shown, the IOL 1 according to the invention includes a central optical component 4 (or optical device), the front surface of which is included on an anterior optical surface 2, and the rear surface of which is included on a rear optical surface 3. The IOL 1 also includes four closed flexible tactile portions 5 (in the form of a mouse ear), each tactile portion forming an annulus based on and connected to the central optical component 4. As explained in the disclosure of the invention, these tactile portions 5 are specifically arranged to stabilize the IOL 1 into the capsular bag of the aphakic eye when the IOL 1 is implanted. Circular extensions 52 of the tactile portions 5 extend around the central optical component 4 for securing the central optical component 4. The diameter d of the central optical component 4, measured perpendicular to the optical axis Z, is between 4.70 mm and 5.00 mm, preferably 4.85 mm. The diameter d' of the central optical component 4 surrounded by the extensions 52, measured perpendicular to the optical axis Z, is between 5.65 mm and 6.10 mm. Preferably, if the optical power of IOL 1 is strictly less than 25D, the diameter d' is between 5.90mm and 6.10mm, more preferably 6.00mm. Preferably, if the optical power of IOL 1 is greater than or equal to 25D, the diameter d' is between 5.65mm and 5.85mm, more preferably 5.75mm. The diameter d” of IOL 1 (including the central optical component 4, the extension 52, and the tactile component 5) measured perpendicular to the optical axis Z is between 10.55mm and 11.20mm. Preferably, if the optical power of IOL 1 is strictly less than 25D, the diameter d” is between 10.80mm and 11.20mm, more preferably 11.00mm. Preferably, if the optical power of IOL 1 is greater than or equal to 25D, the diameter d” is between 10.55mm and 10.95mm, more preferably 10.75mm. Advantageously, the design of the tactile part 5 is adjusted to be a function of the optical power of IOL. The low thickness of the tactile part 5 (between 0.30mm and 0.40mm, measured along the optical axis Z) results in the flexibility of the tactile part 5 and such Figure 1 The positions of these components around the central optical component 4 are such that they are radially deformed to compensate for changes in the capsular size when the IOL 1 is in the implanted state.

[0237] The advantageous aspherical geometry of the front optical surface 2 and the rear optical surface 3 of the IOL 1 according to the invention provides EDOF. Figure 2As shown, IOL 1 focuses light onto an "extended" focal point, while a standard monofocal IOL 1' focuses light onto a single focal point FP. The monofocal IOL 1' provides high-quality vision for selected distant distances around the focal point FP, but not for near and intermediate distances far from that focal point FP. According to the invention, IOL 1 advantageously extends the focal point FP towards a closer distance (asymmetrically) to produce an EDOF, providing better overall quality vision over a wide range of intermediate and far distances.

[0238] To obtain EDOF, the IOL 1 according to the present invention includes a front optical surface 2 and a rear optical surface 3, both of which are aspherical. Figure 3A -D indicates the four different optical powers: 10D (in...) Figure 3A (in China), 15D (in Figure 3B (in China), 20D (in Figure 3C (in) and 35D (in) Figure 3D The cross-sectional profiles (including the optical axis Z) of the front optical surface 2 and the rear optical surface 3 are shown in the figures. For each of these figures, axes 81 and 82 define a Cartesian coordinate system to define the positions of points on the front optical surface 2 and the rear optical surface 3 in the plane showing the cross-sectional profiles. Both axes 81 and 82 are scaled in mm. Axis 81 allows measurement of position along the optical axis Z. Axis 82 allows measurement of position perpendicular to the optical axis Z. Axis 81 and 82 intersect at vertex 21 of the front surface 2. Since the diameter d of the central optical component 4, measured perpendicular to the optical axis Z, is between 4.70 mm and 5.00 mm, it appears... Figure 3A The cross-sectional profile shown in -D is more extended compared to the front optical surface 2 and rear optical surface 3, which were ultimately designed and cut for IOL 1.

[0239] from Figure 3A The derived optical surfaces 2 and 3 define the concave-convex IOL profile. The front optical surface 2 is concave in the front, while the rear optical surface 3 is convex in the rear. Specifically, the radii of curvature R of the front optical surface 2 and the rear optical surface 3 are evaluated at their respective vertices 21 and 31. ant and R post Both are negative, and the quadratic curve constants κ of the front optical surface 2 and the rear optical surface 3 are evaluated at their respective vertices 21 and 31. ant and κ post All are positive. Using the plane perpendicular to the optical axis Z as the zero-elevation reference plane, and the optical axis Z as the reference axis for elevation evaluation, the elevation map evaluated on the radial coordinates of either the front optical surface 2 or the rear optical surface 3 is as follows:

[0240] • It exhibits a local maximum at its vertex 21 or 31.

[0241] • The distance from the vertex 21 or 31 of the optical surface 2 or 3 to its edge (limited to the final cut optical surface 2 or 3, whose size is related to the diameter d) decreases.

[0242] from Figure 3B The optical surfaces 2 and 3 derived by -D define the biconvex IOL profile. The front optical surface 2 is anteriorly convex, while the rear optical surface 3 is posteriorly convex. The radius of curvature R of the front optical surface 2 is evaluated at its vertex 21. ant It is positive, and the radius of curvature R of the rear optical surface 3 evaluated at its vertex 31 is positive. post It is negative, and the quadratic constant κ of the front optical surface 2 evaluated at its vertex 21 is negative. ant It is negative, and the quadratic curve constant κ of the post-optical surface 3 is evaluated at its vertex 31. post It is positive. Using the plane perpendicular to the optical axis Z as the zero-elevation reference plane, and the optical axis Z as the reference axis for elevation evaluation, the elevation map evaluated on the radial coordinates of the front optical surface 2 is as follows:

[0243] • It exhibits a local minimum at its vertex 21.

[0244] • It increases from the vertex 21 of the front optical surface 2 toward its edge (limited to the final cut front optical surface 2, the size of the front optical surface 2 is related to the diameter d).

[0245] Using the plane perpendicular to the optical axis Z as the zero elevation reference plane and the optical axis Z as the reference axis for elevation evaluation, the elevation map evaluated on the radial coordinates of the rear optical surface 3 is presented as follows:

[0246] • Its local maximum value at vertex 31

[0247] • A local minimum 32 is located at a positive distance from the edge of the rear optical surface 3 (limited by the last cut rear optical surface 3, the size of which is related to the diameter d).

[0248] • Inflection point 33 located between the local maximum and the peripheral local minimum 32.

[0249] and:

[0250] • Decrease from its vertex 31 towards the local minimum 32 on the periphery.

[0251] • The value increases from the local minimum 32 on the periphery toward the edge of the rear optical surface 3.

[0252] Given that the elevation map is evaluated on radial coordinates on the rear optical surface 3, its readings at points throughout the rear optical surface 3 (rather than on radial coordinates) define (limit) a loop of such peripheral local minima 32 and a loop of inflection points 33 approximately at the middle optical diameter. These inflection points 33 correspond to the rear optical surface 3 (e.g., ...). Figure 3B -D shows the curvature transition point from concave to convex or from convex to concave. More specifically, the rear optical surface 3 is convex around the vertex 31 and concave around the ring of the peripheral local minimum 32.

[0253] Although the front optical surface 2 and the rear optical surface 3 exhibit obvious curvature changes, it must be noted that both the front optical surface 2 and the rear optical surface 3 are smooth, continuous, and regular. They do not exhibit any discontinuities or incoherent regional limitations.

[0254] The optical power of the IOL 1 according to the invention depends on the refractive index (which is related to the materials constituting the front optical surface 2 and the rear optical surface 3) and the geometry of these surfaces 2 and 3. The geometry of surfaces 2 and 3 is determined by the radius of curvature R. ant and R post and the quadratic curve constant κ ant and κ post Determined (at least around vertices 21 and 31). According to a preferred embodiment of the invention, R is determined if and only if the optical power is greater than or equal to 14D. ant >0, and for all IOLs, R post <0. Radius of curvature R ant The optical power depends continuously and regularly on each of the intervals [0D, 13.5D] and [14D, 40D]. The radius of curvature R post It is continuous and regular, depending on the optical power. This invention advantageously provides new, smooth, continuous, and regular relationships for expressions with respect to the radius of curvature R. ant and R post The function represents the curve constant κ. ant and κ post These are through Figure 5A The graphical representation in -C is used to illustrate this. For each of these figures, axes 83 and 84 define a Cartesian coordinate system, corresponding to the radius of curvature and the quadratic constant, respectively, measured in mm. Figure 5A κ represents the function of the front optical surface 2 of IOL 1 with an optical power greater than or equal to 14D. ant (R ant The graphical representation of the function κ ant (R ant The quadratic curve constant κ is defined. ant Let the radius of curvature be R. ant The function. Figure 5Bκ represents the function κ of the front optical surface 2 of IOL 1 with an optical power strictly less than 14D. ant (R ant The graphical representation of the function κ ant (R ant The quadratic curve constant κ is defined. ant Let the radius of curvature be R. ant The function. Figure 5C The function κ represents the rear optical surface 3 of IOL 1. post (R post ), function κ post (R post The quadratic curve constant κ is defined. post Let the radius of curvature be R. post These are functions. Figure 5A Each point in -C represents both a set of points (or a curve) corresponding to a measured value of the quadratic curve constant, which is a function of the radius of curvature, and a graph of a very good interpolation and / or an approximation of the function of that set of points.

[0255] Figure 5A Graphical representation function

[0256] κ ant (R ant )=-40[erf(0.092R ant- 2.29)+1]

[0257] As can be seen from the graphical representation, it almost perfectly corresponds to the plotted point. This function is novel and very specific in the technical field of this invention. It defines a continuous and regular sigmoid shape, which can be used to define the radius of curvature R of the front optical surface 2 of IOL 1 with an optical power greater than or equal to 14D. ant Any appropriate curve constant κ of the function ant .

[0258] Figure 5B Graphical representation function

[0259]

[0260] As can be seen from the graphical representation, it corresponds to the perfect interpolation of the plotted points (correlation coefficient equal to 1). This function is novel and very specific in the technical field of this invention. It defines a continuous and regular polynomial that can be used to define the radius of curvature R of the front optical surface 2 of IOL1, which has an optical power strictly less than 14D. ant Any suitable curve constant κ of the function ant .

[0261] Figure 5C Graphical representation function

[0262]

[0263] As can be seen from the graphical representation, it corresponds to a near-perfect interpolation (correlation coefficient equal to 0.99) of the plotted points representing, for example, optical powers between 10D and 27.5D. This function is novel and highly specific in the technical field of this invention. It defines a continuous and regular polynomial that can be used to define the radius of curvature R of the rear optical surface 3 as IOL1. post Any suitable curve constant κ of the function post .

[0264] This invention is not limited to the above-mentioned function κ ant (R ant ) and κ post (R post Specific values ​​of the parameters. Any similar sigmoid or polynomial function can be used; the spirit of the invention lies in using these types of relations to represent quadratic curve constants as a function of the radius of curvature of each of the front optical surface 2 and the rear optical surface 3. Examples of similar sigmoid or polynomial functions are provided explicitly or in the form of suitable intervals within the disclosure of this invention, wherein the numerical coefficients of these functions (such as A, B, C, D, a, b, c, f, g, and h as indicated in this document) differ. These intervals do not limit the scope of this disclosure. Furthermore, polynomial functions other than quadratic polynomial functions can be used. For example, Figure 5B The function κ represented in the middle ant (R ant ) can be replaced with

[0265]

[0266] This provides Figure 5B Another very good interpolation for plotting points. However, for computational reasons, a second-order polynomial is preferred. Compared to the aforementioned equation, by reducing the quadratic curve constant of the front optical surface of IOL 1 with an optical power of 13.5, Figure 5B The function κ, represented in the figure, is used for the front optical surface 2 of IOL1 with an optical power strictly less than 14D. ant (R ant It can also be viewed in the form of a very simple first-order polynomial:

[0267] κ ant (R ant = -3.314R ant -38.831

[0268] This simplifies the manufacturing process of IOL 1. Such equations interpolate well the values ​​of a pair of radii of curvature and curve constants of the front optical surface of IOL 1 with a small optical power (i.e., less than or equal to 13.5D), and are very easy to use for computational reasons.

[0269] Figure 6A A graphical representation of the set of points with error bars is shown, corresponding to experimental optical stage measurements of EDOF for IOL 1 as a function of IOL power. The experimental optical stage measurements of EDOF are read on axis 86 and measured in diopters (D). IOL power is read on axis 85 and measured in diopters (D). EDOF is defined as the increase in power from the maximum peak of MTF to an MTF value of 0.17 at 50 Lp / mm. The measurement aperture is 3 mm, and the corneal model provides 0 μm spherical aberration (ISO1). This graphical representation is obtained by polynomial curve interpolation with the following equation.

[0270] EDOF = -0.00002x 3 +0.0004x 2 +0.0288x+0.3104

[0271] Where x is the optical power of the IOL. From Figure 6A As can be seen, the present invention provides an IOL 1 whose EDOF depends on the optical power of the IOL in a very limited manner.

[0272] Figure 6B A graphical representation of the set of points with error bars is shown, corresponding to experimental optical stage measurements of the fourth longitudinal spherical aberration (LSA) of IOL 1 as a function of IOL optical power. These measurements were read on axis 87 and measured in micrometers (μm), while the IOL optical power was read on axis 85 and measured in diopters (D). The SA was measured at 50 Lp / mm and a 4 mm aperture. This graphical representation is obtained by polynomial curve interpolation with the following equation.

[0273] SA = -0.00002x 3 +0.0008x 2 -0.0025x + 0.1982

[0274] Where x is the optical power of the IOL. From Figure 6BAs can be seen, this invention provides an IOL 1 whose SA (autofocus) depends on the optical power of the IOL in a very limited manner. As the optical power decreases, the SA is found to decrease slightly. In fact, lower-power IOLs are actually flatter and more difficult to fabricate aspherically. The EDOF value and SA value follow the same trend; they are strongly correlated.

[0275] Figure 6C A graphical representation of the set of points with error bars is shown, corresponding to experimental optical stage measurements of the MTF of IOL 1 as a function of IOL power. These measurements were read on axis 88 and evaluated at 50 cy / mm, while the IOL power was read on axis 85 and measured in diopter (D). The MTF was measured at 50 Lp / mm and a 3 mm aperture, with the presence of a corneal model providing 0.28 μm spherical aberration (ISO2). This graphical representation can be (very weakly) interpolated using a polynomial curve with the following equation.

[0276] MTF = 0.0006x 2 -0.0222x+0.6994

[0277] Where x is the optical power of the IOL. From Figure 6C As can be seen, the present invention provides an IOL 1 whose MTF depends on the optical power of the IOL in a very limited manner.

[0278] Figure 7 Three graphical representations of the average experimental optical stage measurement of the EDOF of the IOL 1 according to the invention as a function of aperture (here, pupil diameter) are shown. The average experimental optical stage measurement of the EDOF of the IOL 1 is read on axis 86 and measured in diopters (D), and the aperture is read on axis 89 and measured in millimeters (mm). EDOF is defined as the diopter increase from the maximum peak of MTF to an MTF value of 0.17 at 50 Lp / mm. The average of the measurements of an IOL 1 for each diopter of 10D, 15D, 20D, 25D, 30D, and 35D is calculated. The three graphical representations correspond to the use of three different corneal models providing three different corneal spherical aberrations:

[0279] - Provides a corneal model with 0.00 μm corneal spherical aberration (corresponding to reference numeral 71 or ISO1), - Provides a corneal model with 0.13 μm (±0.2 μm) corneal spherical aberration (at a 5.15 mm aperture and IOL plane) (corresponding to reference numeral 72).

[0280] - Provides corneal models with 0.28 μm (±0.2 μm) corneal spherical aberration (at a 5.15 mm aperture and IOL plane) (corresponding to reference numeral 73 or ISO2).

[0281] These graphical representations clearly demonstrate that the EDOF of IOL 1 depends on aperture and corneal spherical aberration in a limited manner. Furthermore, for classic monofocal IOLs known in the art, the widening of the pinhole effect decreases rapidly after pupil dilation, and the resulting EDOF is also reduced accordingly. For IOL 1 according to the invention, this trend is fundamentally different, as the EDOF remains relatively high despite pupil diameter dilation, and this is true for any of the three corneal models described above.

[0282] Figure 8 Three graphical representations of the average experimental optical stage measurement of the MTF of the IOL 1 according to the invention as a function of aperture (here, pupil diameter) are shown. The average experimental optical stage measurement of the MTF is read on axis 88, and the aperture is read on axis 89 and measured in millimeters (mm). The MTF was measured at 50 Lp / mm. The average of the measurements for an IOL 1 at various powers of 10D, 15D, 20D, 25D, 30D, and 35D was calculated. These three graphical representations correspond to the use of the three different corneal models described above (corresponding to reference numerals 71, 72, and 73). These graphical representations show that the MTF of the IOL 1 depends in a limited manner on the aperture and corneal spherical aberration.

[0283] Figure 13 A graphical representation of the defocus MTF curves (corresponding to curves 7A and 7B, respectively) for two IOLs in the intermediate range of (far) optical power (approximately 20D) is shown. These MTFs are read on axis 88 and are presented as a function of the optical power of the IOL, read on axis 85 and measured in diopters (D). The MTFs were measured on an optical stage equipped with a corneal model providing 0.00 μm spherical aberration (ISO1) at 50 Lp / mm and a 3 mm aperture. Curves 7A and 7B correspond to the MTF measurements for a standard monofocal IOL and IOL1, respectively. The elongated focal length of IOL 1 according to the invention... Figure 13 As can be seen, in the case of the IOL 1 according to the invention, an asymmetric MTF peak is clearly shown, with an elongated focal point toward higher power (closer distance), while the MTF peak of a standard monofocal lens is substantially symmetrical with respect to the focal power at the optimal focal point, which is allocated to the far distance. As demonstrated on an optical workbench, these differences illustrate the superior EDOF and better clinical visual acuity of the IOL 1 according to the invention at mid-range distances.

[0284] Figure 9AThe figures in -C show graphical representations of experimental optical stage measurements of fourth-order spherical aberration (hereinafter referred to as SA) as a function of aperture (which is the pupil diameter), read on axis 90 and measured in micrometers (μm), while the aperture is read on axis 89 and measured in millimeters (mm). For each of these figures, SA is measured at 50 Lp / mm for:

[0285] - One of the three corneal models described above, considered individually (corresponding to figure 74).

[0286] -IOL 1 according to the invention (corresponding to reference numeral 75) considered separately

[0287] - The specific corneal model combined with the IOL 1 (corresponding to reference numeral 76)

[0288] Figure 9A , 9B The corneal models considered in 9C are:

[0289] - Provides a corneal model with 0.28μm (±0.2μm) corneal spherical aberration (5.15mm aperture, IOL plane).

[0290] - Provides a corneal model with 0.13μm (±0.2μm) corneal spherical aberration (5.15mm aperture, IOL plane), and

[0291] - Provides a corneal model with 0.00μm corneal spherical aberration.

[0292] The difference between IOL 1 and conventional monofocal IOLs lies in the amount of sarcoplasmic reticulum (SA) it provides. IOL 1 has a negative SA, which decreases rapidly with aperture. Compared to the SA of conventional monofocal IOLs, IOL 1 has a more negative SA. Therefore, the SA produced by any combination of corneal model and IOL 1 is essentially determined by the SA of that IOL 1, as the SA of IOL 1 overcompensates for the (small) positive SA of any corneal model. The residual SA is then advantageously affected only very slightly by the choice of corneal model.

[0293] After the presence of EDOF in the IOL 1 according to the invention, the combined optical refraction of the anterior optical surface 2 and the rear optical surface 3 with the average corneal model (preferably, as defined in paragraph

[0049] ) (arranged in front of the optical axis Z relative to the IOL 1) provides a continuous and regular optical power, as shown in Figure 9. This Figure 9 includes a central global maximum value 91 along the optical axis Z, which is surrounded by an extended central region 92 of lower optical power (corresponding to EDOF). Within a (reading) window centered on the optical axis Z and with a diameter of 4 mm, Figure 10A and10B Figure 9 shows IOL power values ​​of 35D and 20D respectively. Recall that the IOL power is defined as the uncorrected average power measured within a (reading) window with a diameter of 3mm centered on the optical axis (this power is represented by Figure 9). The central region 92 extends over approximately half the diameter d of the front optical surface 2 and the rear optical surface 3, and is marked by the points in Figure 9 (these points are inflection points). Figure 10A In the case of) or the local minimum of optical power (in) Figure 10B In both cases, the first rings 93 and 93' surround the area. These first rings 93 and 93' correspond to the radial variation trend of optical power. Figure 10B Figure 9 more realistically illustrates this general optical power of approximately 20D. In this case, Figure 9 also includes:

[0294] -The first ring 93, which is the local minimum of the optical power around the extended central region 92, and

[0295] - The second ring 94 is the local maximum value of the optical power around the first ring 93.

[0296] More generally, according to some embodiments of the invention, the IOL 1 comprises a set of rings (e.g., rings 93 and 94) with gradually alternating maximum and minimum optical powers. It must be noted that the optical power of any IOL is very smooth, continuous, and regular. It is not divided into zones based on fixed optical powers.

[0297] exist Figure 11A (For an optical power equivalent to 10D) Figure 11B (for an optical power equivalent to 24D) and Figure 11C (For an optical power equal to 35D) a cross-sectional representation of the IOL 1 according to a preferred embodiment of the invention is also shown. These IOL 1 sections are formed along a plane including the optical axis z. Figure 11A The geometry and concave or convex shape of the aforementioned front optical surface 2 and rear optical surface 3 can be seen in -C. These front optical surfaces 2 and rear optical surfaces 3 are separated by an inner body 41 of a central optical component 4 made of biomaterials. The inner body 41 has a predetermined central thickness E measured along the optical axis Z, which is between 0.3 mm and 0.7 mm and regularly depends on the optical power of the IOL, thus providing an IOL peripheral thickness between 0.2 mm and 0.3 mm (preferably about 0.25 mm) for connecting the flexible tactile part 5 to the central optical component 4.

[0298] like Figure 12AAs shown, the central optical component 4 of IOL 1 preferably has a principal optical plane (M) that is separated from the top edge (51) of the flexible tactile interface (5) by a predetermined distance (HC) measured along the optical axis (Z), the predetermined distance (HC) being between 0.00 mm and 0.45 mm. This distance (HC) depends continuously and regularly on the optical power of IOL 1 by a function, the graph of which is shown in [the figure]. Figure 12B In the middle, a distance (HC) measured in millimeters (mm) is read on axis 62, which is a function of optical power measured in diopters (D) and read on axis 61. This function increases continuously with increasing optical power, and its graph exhibits an S-shaped profile. Given the geometry of the anterior optical surface 2 and the posterior optical surface 3, this distance (HC) is advantageously calculated to ensure a longitudinally stable (unchanging with the optical power) position of the principal optical plane of IOL 1 relative to the optical axis Z when IOL 1 is implanted in the eye.

[0299] In other words, the present invention relates to an intraocular lens 1 with extended depth of focus, comprising an aspherical anterior optical surface 2 and a posterior optical surface 3. The specific aspherical geometries of these optical surfaces 2 and 3 are described within the framework of this invention.

[0300] The invention has been described with reference to specific embodiments, which are of illustrative value only and should not be considered limiting. Those skilled in the art will note that the invention is not limited to the examples shown and / or described above. The invention includes each of the technical features described in this document and combinations thereof.

Claims

1. An artificial lens (1), comprising: - Front optical surface, and - Back optical surface Both the front and rear optical surfaces extend radially outward relative to the optical axis (Z); Its features are: -The first surface (2) of the front optical surface and the rear optical surface is defined by the following equation: in: ●z st (r) is a component of the displacement vector measured along the optical axis (Z) from the vertex (21) of the first surface (2) to any point on the first surface (2). The distance between any point on the first surface (2) and the optical axis (Z) is a radius r; ●R st It is the radius of curvature of the first surface (2) evaluated at the vertex (21); ●κ st (R st ) is the quadratic curve constant of the first surface (2) evaluated at the vertex (21), and is defined as the radius of curvature R of the first surface (2) by the following relationship. st Functions: Where erf represents the Gaussian error function, and a, b, c, A, B, C, and D are constant real numbers such that: a∈[0.050; 0.075], b∈[-1; 0], c∈[-20; 0], A∈[-41; -39], B∈[0.07; 0.13], C∈[-2.6; -2.0], and D∈[0.75; 1.25] ● It is the 2i-th order aspherical coefficient of the first surface (2); -A second surface (3), which is between the front and rear optical surfaces and is different from the first surface (2), is defined by the following equation: in: ●Z nd (r) is a component of the displacement vector measured along the optical axis (Z) from the vertex (31) of the second surface (3) to any point on the second surface (3). Any point on the second surface (3) is a radius r away from the optical axis (Z); ●R nd <0 is the radius of curvature of the second surface (3) evaluated at the vertex (31); ●κ nd (R nd ) is the quadratic curve constant of the second surface (3) evaluated at the vertex (31), and is defined as the radius of curvature R of the second surface (3) by the following relationship. nd Functions: Where f, g, and h are constant real numbers such that: f∈[0.08; 0.12], g∈[1.0; 1.6], h∈[0; 9]; ● It is the 2i-th order aspherical coefficient of the second surface (3); Wherein, the aspheric coefficients of the first surface (2) and the second surface (3) of order less than or equal to 10 are all non-zero, and the absolute values ​​of the aspheric coefficients of order less than or equal to 10 are all bounded by 0.1; The aspheric coefficients of the first surface (2) and the second surface (3) that are strictly greater than 10 are equal to zero; The anterior and posterior optical surfaces enable the artificial lens (1) to provide an extended depth of focus.

2. The intraocular lens (1) according to claim 1, characterized in that: a∈[0.060; 0.075] and / or b∈[-0.5; -0.2] and / or c∈[-12; -10] and / or A∈[-40.1; -39.9] and / or B∈[0.080; 0.095] and / or C∈[-2.35; -2.05] and / or D∈[0.90; 1.1] and / or f∈[0.085; 0.105] and / or g∈[1.05; 1.40] and / or h∈[3; 6].

3. The intraocular lens (1) according to any one of claims 1 to 2, characterized in that: If R st >0; If R st <0; Where, for each j∈{1,2,3}, p j ≥10.

4. The intraocular lens (1) according to any one of claims 1 to 2, characterized in that, The optical power of the artificial lens (1) is between 10D and 35D.

5. The intraocular lens (1) according to any one of claims 1 to 2, characterized in that: - The optical power of the artificial lens (1) is strictly less than 14D, and R st <0; or -The optical power of the artificial lens (1) is greater than or equal to 14D, and R st >0.

6. The intraocular lens (1) according to any one of claims 1 to 2, characterized in that... and / or 7. The intraocular lens (1) according to any one of claims 1 to 2, characterized in that, The first surface (2) is the front optical surface, the second surface (3) is the rear optical surface, and the optical axis (Z) points from the front optical surface to the rear optical surface.

8. The intraocular lens (1) according to claim 7, characterized in that, The optical power of the artificial lens (1) is 15D, and wherein: R st =79.63mm and / or κ st (R st = -80.00 and / or and / or and / or and / or and / or R nd＝ -13.82mm and / or κ nd (R nd ) = 5.95 and / or and / or and / or and / or 9. The intraocular lens (1) according to claim 7, characterized in that, The optical power of the artificial lens (1) is 20D, and wherein: R st =21.60mm and / or κ st (R st ) = -25.61 and / or and / or and / or and / or and / or R nd = -15.21mm and / or κ nd (R nd = 8.10 and / or and / or and / or and / or 10. The intraocular lens (1) according to claim 7, characterized in that, The optical power of the artificial lens (1) is 25D, and wherein: R st =11.47mm and / or k st (R st ) = -3.67 and / or and / or and / or and / or and / or R nd = -19.47mm and / or k nd (R nd ) = 17.61 and / or and / or and / or and / or 11. The intraocular lens (1) according to claim 7, characterized in that, The artificial lens (1) has an optical power greater than or equal to 14D, and is characterized in that: - Using the plane perpendicular to the optical axis (Z) as the zero elevation reference plane and the optical axis (Z) as the reference axis for elevation evaluation, the elevation map evaluated on the radial coordinates of the first surface (2) is as follows: ● A local minimum is observed at the vertex (21) of the first surface (2). ●Incrementing from the vertex (21) of the first surface (2) to the edge of the first surface (2); -Using the plane perpendicular to the optical axis (Z) as the zero elevation reference plane and the optical axis (Z) as the reference axis for elevation evaluation, the height map evaluated on the radial coordinates of the second surface (3) is presented: ●The local maximum value at the vertex (31) of the second surface (3), ● The peripheral local minimum (32) at a positive distance from the edge of the second surface (3), ● The inflection point (33) between the local maximum and the peripheral local minimum (32), and: ●The value decreases from the vertex (31) of the second surface (3) to the peripheral local minimum (32). ●Increment from the peripheral local minimum (32) to the edge of the second surface (3).

12. The intraocular lens (1) according to claim 7, characterized in that, The optical power of the artificial lens (1) is strictly greater than 12D and strictly less than 14D, and is characterized in that: -Using the plane perpendicular to the optical axis (Z) as the zero elevation reference plane and the optical axis (Z) as the reference axis for elevation evaluation, the elevation map evaluated on the radial coordinates of the first surface (2) is presented as follows: ●The local maximum value at the vertex (21) of the first surface (2), ●The local minimum value at a positive distance from the edge of the first surface (2) is located on the periphery. ● The inflection point located between the local maximum value and the peripheral local minimum value. and: ●The local minimum value decreases from the vertex (21) of the first surface (2) to the periphery. ●Increases from the local minimum value on the periphery to the edge of the first surface (2). -Using the plane perpendicular to the optical axis (Z) as the zero elevation reference plane and the optical axis (Z) as the reference axis for elevation evaluation, the elevation map evaluated on the radial coordinates of the second surface (3) is presented as follows: ●The local maximum value at the vertex (31) of the second surface (3), ● The peripheral local minimum (32) at a positive distance from the edge of the second surface (3), ● The inflection point (33) between the local maximum and the peripheral local minimum (32), and: ●The value decreases from the vertex (31) of the second surface (3) to the peripheral local minimum (32). ●Increment from the peripheral local minimum (32) to the edge of the second surface (3).

13. The intraocular lens (1) according to claim 7, characterized in that, The optical power of the artificial lens is less than or equal to 12D, and is characterized in that: - Using the plane perpendicular to the optical axis (Z) as the zero elevation reference plane and the optical axis (Z) as the reference axis for elevation evaluation, the elevation map evaluated on the radial coordinates of the first surface (2) is as follows: ● A local maximum value is observed at the vertex (21) of the first surface (2). ●The distance decreases from the vertex (21) of the first surface (2) to the edge of the first surface (2); - Using the plane perpendicular to the optical axis (Z) as the zero elevation reference plane and the optical axis (Z) as the reference axis for elevation evaluation, the elevation map evaluated on the radial coordinates of the second surface (3) is as follows: ●A local maximum value is observed at the vertex (31) of the second surface (3). ● The gradient decreases from the vertex (31) of the second surface (3) to the edge of the second surface (3).

14. The intraocular lens (1) according to any one of claims 1 to 2, characterized in that, The front and rear optical surfaces are cut from hydrophobic biomaterials with refractive indices between 1.40 and 1.

65.

15. The intraocular lens (1) according to any one of claims 1 to 2, characterized in that, The front optical surface and the rear optical surface are separated by an inner body (41) of a predetermined center thickness (E), measured along the optical axis (Z), the predetermined center thickness being between 0.30 mm and 0.70 mm.

16. The intraocular lens (1) according to any one of claims 1 to 2, characterized in that, Both the front optical surface and the rear optical surface have a diameter (d) measured perpendicular to the optical axis (Z), and the diameter (d) is between 4.70 mm and 5.00 mm.

17. The intraocular lens (1) according to any one of claims 1 to 2, characterized in that, The combined optical refraction of the anterior and posterior optical surfaces with the corneal model on the anterior exterior of the intraocular lens (1) provides a continuous and regular graph (9) of optical power, the graph (9) including a central global maximum value (91) along the optical axis (Z), the central global maximum value (91) being surrounded by an extended central region (92) of lower optical power.

18. The intraocular lens (1) according to claim 17, characterized in that, The central region (92) extends over approximately half the diameter (d) of the front and rear optical surfaces and is surrounded by a first ring (93, 93') of the point in Figure (9), which is an inflection point or local minimum of optical power.

19. The intraocular lens (1) according to claim 18, characterized in that, The figure (9) further includes a second ring (94) of the point of local maximum optical power, the second ring (94) surrounding the first ring (93).

20. The intraocular lens (1) according to any one of claims 1 to 2, characterized in that, The intraocular lens includes: - Central optical component (4), the front surface of the central optical component (4) is the front optical surface, and the rear surface of the central optical component (4) is the rear optical surface; - A plurality of flexible tactile parts (5), the plurality of flexible tactile parts (5) being connected to the central optical component (4) and configured to stabilize the artificial lens (1) into the capsular bag of the aphakic eye.

21. The intraocular lens (1) according to claim 20, characterized in that, The distance (HC) between the top end (51) of the flexible tactile part (5) and the principal optical plane (M) of the central optical component (4), measured along the optical axis (Z), corresponds to the image of the optical power of the intraocular lens (1) by a continuous regular function. The distance (HC) increases continuously with the increase of optical power and is bounded at 0.45 mm, so that when the intraocular lens (1) is implanted into the capsular bag of the aphakic eye, the principal optical plane (M) is stably parallel to the optical axis (Z).

22. The intraocular lens (1) according to claim 20, characterized in that, The artificial lens (1) includes four closed flexible tactile portions (5), each flexible tactile portion (5) forming a ring based on the central optical component (4).

23. The intraocular lens (1) according to any one of claims 1 to 2, characterized in that, The shape of the artificial lens (1) remains unchanged after rotating 180° around the optical axis (Z).

24. A method for manufacturing an intraocular lens (1) according to any one of claims 1 to 23, characterized in that, The manufacturing method includes the following steps: (a) Modeling optical devices with cross-sectional configurations of aspherical optical surfaces; (b) Calculate the refractive efficiency distribution of light propagating through the modeled optical device; (c) Select the profile parameters of the aspherical optical surface based on the calculated refractive efficiency distribution. In order to obtain the desired refractive efficiency; and (d) Forming biomaterials into modeled optical devices with selected parameters.

25. The manufacturing method according to claim 24, characterized in that, The profile parameters of the aspherical optical surface selected in step (c) are continuously and regularly dependent on the optical power of the artificial lens (1).

26. The manufacturing method according to any one of claims 24 to 25, characterized in that, In step (c), the quadratic curve constant κ of the first surface (2) among these aspherical optical surfaces is selected. st The quadratic curve constant κ st For evaluation at the vertex of the first surface (2), the quadratic curve constant κ is obtained through the following relationship. st The radius of curvature R of the first surface (2) evaluated at the vertex (21) of the first surface (2) st Functions: Where erf represents the Gaussian error function, and a, b, c, A, B, C, and D are constant real numbers; and in step (c), the quadratic curve constant κ of the second surface (3) among these aspherical optical surfaces is selected. nd The quadratic curve constant κ st For evaluation at the vertex of the second surface (3), the quadratic curve constant κ is obtained through the following relationship. nd The radius of curvature R of the second surface (3) evaluated at the vertex (31) of the second surface (3) nd Functions: Where f, g, and h are constant real numbers.

27. The manufacturing method according to any one of claims 24 to 25, characterized in that, The intraocular lens (1) is the intraocular lens (1) according to claim 21, and is characterized by selecting a distance (HC) by a continuous and regular function, the distance (HC) being a function of the optical power of the intraocular lens (1) as an image of optical power, the distance (HC) being the distance between the top end (51) of the flexible tactile part (5) and the principal optical plane (M) of the central optical component (4) measured along the optical axis (Z), the distance (HC) increasing continuously with increasing optical power and bounded by 0.45 mm. In order to achieve the desired longitudinal stability of the principal optical plane (M) parallel to the optical axis (Z) when the artificial lens (1) is implanted into the capsular bag of the aphakic eye.

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