Extended depth of focus ophthalmic lens, design method thereof, and manufacturing method thereof

Abstract

The present invention provides an intraocular lens and related technologies, which have regions concentric with a lens center O, including at least one distance region for correcting visual acuity for distance vision and at least one near region for correcting visual acuity for near vision, wherein the power in the distance region is reduced to provide a negative vertical spherical aberration that at least partially offsets the positive vertical spherical aberration caused by the cornea, and the near region has a predetermined base power at the lens center O and adds a positive fixed power to an aspherical reference power within a predetermined radial range of a virtual aspherical lens that completely offsets the positive vertical spherical aberration caused by the cornea, and the near region has at least three sub-regions arranged radially, wherein sub-region 1 provides a positive power deviation for the positive fixed power, sub-region 2 provides an approximately zero power deviation for the positive fixed power, and sub-region 3 provides a negative power deviation for the positive fixed power.

Description

[Technical Field]

[0001] The present invention relates to an intraocular lens, a method for designing an intraocular lens, a method for manufacturing an intraocular lens, an ophthalmic lens, an optical design method for an ophthalmic lens, and a method for manufacturing an ophthalmic lens. For example, the present invention relates to an ophthalmic lens having a base power for correcting (visual acuity of) distance vision and an add power for correcting (visual acuity of) near vision and / or intermediate vision.

[0002] The present invention relates to a novel optical design for an intraocular lens (IOL), a phakic intraocular lens (or implantable contact lens (ICL), the term "implantable" being omitted hereafter), that can be used to correct not only distance vision but also near and / or intermediate vision. This disclosure will focus in detail on intraocular lenses only, as they are representative of various ophthalmic lenses. However, the present invention is applicable to the optical designs of phakic intraocular lenses and contact lenses as well. [Background technology]

[0003] In addition to correcting distance vision, IOLs with add power can also be used to correct near and / or intermediate vision in aphakic patients.

[0004] In this specification, the term "add power" is also referred to as "positive power addition." The use of the term "add power" is not limited to ophthalmic lenses that have an add power (ADD) as a prescription value.

[0005] As used herein, the term "extended vision range IOL" refers to an IOL that has a base power to correct distance vision and an add power to correct near and / or intermediate vision. Extended vision range IOLs are also referred to herein as "EVR IOLs."

[0006] Although the present specification exemplifies the case of far-distance vision as being at infinity, it is also possible to consider the case of viewing an object at a finite distance (1.5 m or more (far distance)) instead of at infinity. Intermediate vision may be considered as viewing an object at a distance of 1.5 m to 50 cm (intermediate distance). Near vision may be considered as viewing an object at a distance of 50 cm or less (near distance). In any case, seeing a distance farther than near vision is called intermediate vision, and seeing a distance farther than intermediate vision is called distance vision.

[0007] The lens center O refers to the geometric center or optical center of the intraocular lens. In this specification, the case where the geometric center and the optical center coincide is illustrated. The refractive power at this lens center O is referred to as the base power. This base power refers to the refractive power required for distance vision in the conventional intraocular lens.

[0008] EVR IOLs, which obtain add power by applying the principles of refractive optics, can be classified into bifocal and multifocal types. Bifocal intraocular lenses (bifocal lenses) implanted in the eyes of aphakic patients tend to have two primary focal lengths: one focal length is designed to focus distant light rays to correct distance vision (distance vision), and the other focal length is designed to focus near light rays to correct near vision (near vision). Multifocal intraocular lenses (IMLs) implanted in aphakic patients' eyes provide three or more focal lengths, typically one for distance vision correction and two or more for near and intermediate vision correction.

[0009] The first focal length of an EVR IOL used to correct distance vision relates to the base power of the IOL, i.e., corresponds to the prescribed spherical power (labeled refractive power) of the IOL, e.g., 20.0 D (unit: diopter, hereafter the same). The second focal length, used to correct near and / or intermediate vision, corresponds to the sum of the base power (labeled refractive power) and the add power of the IOL. For example, if the IOL has an add power of 3.0D, the second focal length corresponds to a power value of 23.0D (the sum of the labeled refractive power of 20.0D and the add power of 3.0D).

[0010] Refractive EVR IOLs can be classified into three IOL types (see, for example, Patent Document 1, WO2021 / 111821, filed by the present applicant). For details not described in this specification, please refer to the details described in Patent Document 1. One of these three types is, for example, an enhanced monofocal IOL (commonly known as an EM-IOL), which has one or more added positive fixed powers of 1.25D or less. Another example is a multifocal lens (for example, one or more added positive fixed powers, i.e., an add power of 2.5D or more). Another example is an extended depth-of-focus IOL (commonly known as an EDOF), which is an intermediate lens between the two (for example, one or more added positive fixed powers greater than 1.25D and less than 2.5D (e.g., 2D)). Note that the classification in this paragraph is merely an example, and for example, a case where there are two types of positive fixed powers, one value being 1.25D or less and the other value being greater than 1.25D but less than 2.5D, is not excluded from the present invention.

[0011] EM-IOLs are designed to correct distance and intermediate vision, for example. Typically, this IOL type has an add power of 1.25 to 2.0 D at the IOL surface (approximately 0.9 to 1.4 D at the corneal surface). EDOF lenses are designed to correct distance, intermediate, and slight near vision. Typically, their add power is 2.0-2.75D of surface power (approximately 1.4-1.9D at the corneal surface). Multifocal lenses are designed to correct distance, intermediate, and near vision, usually with an add power greater than 2.75 D of surface power (greater than 1.9 D at the corneal surface).

[0012] A disadvantage of bifocal lenses is the narrow range of near distances at which an aphakic patient's eye can clearly see objects, resulting in a short near-distance range of near vision. This narrow near-distance range is particularly evident in bifocal IOLs, which have a relatively constant add power in the zone of the lens dedicated to near vision correction. Furthermore, bifocal IOLs with a relatively large zone of near vision correction have a disadvantage in that the lens zone dedicated to distance vision correction is small, resulting in a loss of image quality (sharpness and contrast) for distance vision.

[0013] When implanted in an aphakic patient's eye, a bifocal EVR IOL with strong bifocal properties can provide the wearer with sharp images of two objects at different distances. One sharp distance image (the image of an object located at a distance reconstructed on the retina) and one sharp near image (the image of an object located at a near distance reconstructed on the retina) are visible to the aphakic patient. However, objects immediately adjacent to the cornea can be clearly seen by the aphakic patient's eye if only light rays from the object are focused onto the retina by the corneal optics and the EVR IOL. To be focused on the retina, the distance of the nearby object in front of the cornea must be within a specific near-distance range. This specific near-distance range in which near objects are still visible is clearly related to the EVR IOL's add power and power profile (also known as radial power or power distribution). A power profile is, for example, a graph with radius (in mm) on the horizontal axis and power (in diopters) (in D) on the vertical axis. This type of graph shows the power value at a specific radius value, which is the radial distance from the lens center O in the IOL.

[0014] There are many bifocal type EVR IOLs disclosed in the patent literature.

[0015] US Pat. No. 4,636,211 discloses a bifocal IOL with a two-zone design, which includes a central region for correcting near vision and an annular region surrounding the central region for correcting distance vision.

[0016] Patent document 3 (US Pat. No. 5,192,317) discloses a three-zone IOL having a central region for correcting distance vision, a first annular region surrounding the central region for correcting near vision, and a second annular region surrounding the first annular region for correcting distance vision.

[0017] Patent document 4 (US Pat. No. 4,813,955) discloses a four-zone intraocular lens having a central region, a first annular region, a second annular region, and a third annular region each having the function of correcting distance vision, far vision, and near vision.

[0018] Patent Document 5 (WO1997 / 26843) discloses a five-zone IOL with a central zone, a second annular zone, and a fourth annular zone for correcting distance vision, and a first annular zone and a third annular zone for correcting near vision. The advantage of a bifocal lens is that it can form two sharp images on the retina, one of which is a sharp image of a limited range of near objects, and the other is a sharp image of a far-distance object.

[0019] Other patents disclose IOLs with one or more zones for correcting distance vision and one or more zones for correcting near vision, with one or more transition zones between the zones for correcting distance vision and the zones for correcting near vision. Examples of these patents are U.S. Pat. No. 5,112,351 (US Pat. No. 5,112,351), U.S. Pat. No. 5,094,231,2 B1 (EP Pat. No. 5,094,231,2 B1), and U.S. Pat. No. 6,457,826 (US Pat. No. 6,457,826). The IOLs described in these patents can improve image quality for intermediate vision. However, image quality for near vision is lower than that of bifocal IOLs. Image quality for distance vision is also lower than that of bifocal lenses. The reason for this poor image quality for distance and near vision is due to the transition zone or power of the transition zone, as characterized in these patents. That is, light rays from intermediate distances that are focused on the retina reduce the number of light rays from near distances, which reduces the number of light rays from far distances that must reconstruct the image for distance vision on the retina.

[0020] Common EVR IOLs in the refractive bifocal type have two-zone and three-zone optical designs. A two-zone optical design IOL has two zones: the inner zone (the first zone containing the center of the lens) has a power greater than the power of the outer zone, which is used to correct near vision, and the outer zone has a base power to correct distance vision. A three-zone optical design IOL has three zones: Zone 1, which includes the center of the lens, is used to correct distance vision; Zone 2, which is an annular zone surrounding Zone 1 and has a power greater than the base power, is used to correct near vision; and Zone 3, which is an annular zone surrounding Zone 2 and is used to correct distance vision. The optical characteristics and performance of bifocal two-zone and bifocal three-zone IOLs for correcting distance and near vision in aphakic eyes depend on the add power and power profile of the IOLs. [Prior art documents] [Patent documents]

[0021] [Patent Document 1] WO2021 / 111821 publication [Patent Document 2] US4636211 specification [Patent Document 3] US5192317 statement [Patent Document 4] US4813955 specification [Patent Document 5] WO97 / 026843 publication [Patent Document 6] US5112351 specification [Patent Document 7] EP0942312B1 specification [Patent Document 8] US6457826 specification Summary of the Invention [Problem to be solved by the invention]

[0022] For example, new power profiles for bifocal EVR IOLs are disclosed herein, which can include two-zone and three-zone optical designs.

[0023] The power profiles disclosed herein can improve the optical properties and performance of, for example, bifocal EVR IOLs for correcting distance and near vision in aphakic patients.

[0024] The objective of one aspect of the present invention is to increase the depth of focus for near and / or intermediate vision and / or improve the image quality for distance vision compared to the specific examples below to which the present invention is not applied (listed as "Flat"). [Means for solving the problem]

[0025] According to a first aspect of the present invention, there is provided a lens having at least one distance region for correcting vision for distance vision and at least one near region for correcting vision for near vision, the distance region and the near region being concentric with a lens center O, In the distance region, the optical power of the lens decreases as the radial distance to the lens center O increases; the near region comprises at least three radially aligned sub-regions; The sub-region 1 provides a positive power deviation to a virtual optical power profile in a near region, the virtual optical power profile being an aspheric power profile to which a positive constant power is added; Subregion 2 provides zero power deviation with respect to the virtual optical power profile; Sub-region 3 provides a negative power deviation relative to the virtual optical power profile, with which an intraocular lens is provided. In other words, subregion 1 provides a positive power deviation for a positive constant power, subregion 2 provides a zero power deviation for a positive constant power, and subregion 3 provides a negative power deviation for a positive constant power. IOLs with these three subzones in the near region were found to lead to an extended depth of focus for near vision. Preferably, in subregion 2, the power deviation is considered to be zero when the average power deviation in subregion 2 is in the range of -0.2 to 0.2 D. For this reason, a power deviation of zero can also be considered to be a power deviation of approximately zero. The distance region, in which the optical power of the lens decreases with increasing radial distance to the lens center O, can also be considered a distance region with decreasing power. Preferably, in the distance region, the optical power of the lens decreases with increasing radial distance to the lens center O, i.e., the distance region decreases in power to at least partially offset the positive vertical spherical aberration of the human cornea with negative vertical spherical aberration. Thus, preferably, in the distance region, the decrease in optical power with increasing radial distance to the lens center, i.e., the corresponding power profile, is such that the positive vertical spherical aberration of the human cornea is at least partially offset. This allows for improved distance vision. In one example, the human cornea is an average human cornea. Thus, in one example, the distance region decreases in power, i.e., the optical power decreases with increasing radial distance to the lens center in the distance region, due to the positive vertical spherical aberration of the average human cornea being at least partially offset by negative vertical spherical aberration. The average human cornea is an average of several human corneas. The average human cornea can be any average of human corneas. For example, the average can correspond to the cornea of ​​a human eye model in optical design software such as Zemax®, particularly Zemax® 13. The average cornea may correspond to the corneas listed in Table 1 herein. Preferably, the aspheric power profile (which may also be considered as an aspheric reference power) of the virtual optical power profile can be described as having a base power at the lens center O, and in the near zone, a positive constant power is added to the aspheric reference power to form a virtual optical power profile that may also be considered as a power profile of a virtual aspheric lens. In other words, the near zone has a base power at the lens center O, and a positive constant power is added to the aspheric reference power between a predetermined radial range of the virtual aspheric lens. The virtual optical power profile in the near zone is preferably such that the positive vertical spherical aberration of the human cornea, particularly the average human cornea, is compensated for. This compensation can be partial or complete. Thus, in one embodiment, the near zone has a predetermined base power at the lens center O, and a positive constant power is added to the aspheric base power over a predetermined radial range of the virtual aspheric lens to fully compensate for the positive vertical spherical aberration of the average human cornea. Thus, the first aspect is: The lens has at least one distance area for correcting vision for distance vision and at least one near area for correcting vision for near vision, the distance area being concentric with the lens center O; reducing the power in the distance region to provide a negative longitudinal spherical aberration that at least partially offsets the positive longitudinal spherical aberration caused by the cornea; In the near area, a positive constant power is added to an aspherical reference power within a predetermined radial range of a virtual aspherical lens having a predetermined base power at the lens center O and completely offsetting the positive vertical spherical aberration caused by the cornea, the near region comprises at least three radially aligned sub-regions; Subregion 1 provides a positive power deviation from the positive constant power, Sub-region 2 provides zero power deviation, in particular nearly zero power deviation, relative to the positive constant power, Sub-region 3 is an intraocular lens that provides a negative power deviation from the positive constant power. The power reduction of the aspheric power profile in the near zone is preferably equal to the power reduction in the distance zone, in other words, in one example, the optical power in the distance zone decreases with increasing radial distance to the lens center in line with the reduction of the aspheric power profile of the virtual optical power profile in the near zone.

[0026] The near distance region may include the lens center O, and the far distance region may be located outward from the near distance region. The lens has a near area that is concentric with the lens center O and includes the lens center O and corrects visual acuity for near vision, and a far area that is disposed radially outward from the lens center O and corrects visual acuity for far vision, reducing the power in the distance region to provide a negative longitudinal spherical aberration that at least partially offsets the positive longitudinal spherical aberration caused by the cornea; In the near area, a positive constant power is added to an aspherical reference power within a predetermined radial range of a virtual aspherical lens having a predetermined base power at the lens center O and completely offsetting the positive vertical spherical aberration caused by the cornea, the near region comprises at least three radially aligned sub-regions; Subregion 1 provides a positive power deviation from the positive constant power, Sub-region 2 provides zero power deviation, in particular nearly zero power deviation, relative to the positive constant power, Sub-region 3 is an intraocular lens that provides a negative power deviation from the positive constant power.

[0027] According to a third aspect of the present invention, a ophthalmic lens includes a distance region including a lens center O and correcting vision for distance vision, and an outer region disposed radially outward from the lens center O and further outward than a near region correcting vision for near vision, and correcting vision for distance vision, wherein the distance region, the near region, and the outer region are concentric with the lens center O, i.e., they start from the lens center O and face away from the lens center O in the radial direction, and the order of the regions is the distance region, the near region, and the outer region; In said outer region, the optical power of the lens decreases with increasing radial distance to the lens center O; the near region comprises at least three radially aligned sub-regions; subregion 1 provides a positive power deviation to the virtual optical power profile in the near region, which is an aspheric power profile plus a positive constant power, i.e., said virtual optical power profile is an aspheric power profile plus a positive constant power, Subregion 2 provides zero power deviation with respect to the virtual optical power profile; Sub-region 3 provides a negative power deviation relative to the virtual optical power profile, with which an intraocular lens is provided. In other words, subregion 1 provides a positive power deviation for a positive constant power, subregion 2 provides a zero power deviation for a positive constant power, and subregion 3 provides a negative power deviation for a positive constant power. An IOL with these three subzones in the near zone can lead to an extended depth of focus for near vision, and the inner distance zone, combined with the outer zone, can lead to improved image quality for distance vision. Preferably, in subregion 2, the power deviation is considered to be zero when the average power deviation in subregion 2 is in the range of -0.2 to 0.2 D. For this reason, a power deviation of zero can also be considered to be a power deviation of approximately zero. The distance region, in which the optical power of the lens decreases with increasing radial distance to the lens center O, can also be considered a distance region of decreasing power. Preferably, in the outer region, the optical power of the lens decreases with increasing radial distance to the lens center O, i.e., the outer region decreases in power to at least partially offset the positive vertical spherical aberration of the human cornea with negative vertical spherical aberration. Thus, preferably, in the outer region, the decrease in optical power with increasing radial distance to the lens center, i.e., the corresponding power profile, is such that the positive vertical spherical aberration of the human cornea is at least partially offset. This allows for further improved distance vision. As explained above, in one example, the human cornea is an average human cornea. Thus, in one example, the outer region has a decreasing power, i.e., the optical power decreases with increasing radial distance to the lens center in the outer region to at least partially offset the positive vertical spherical aberration of the average human cornea with negative vertical spherical aberration. The average human cornea is an average of several human corneas. The average human cornea can be any average of human corneas. For example, the average can correspond to the cornea of ​​a human eye model in optical design software such as Zemax®, particularly Zemax® 13. The average can correspond to the corneas listed in Table 1 herein. Preferably, the aspheric power profile (which may also be considered as an aspheric reference power) of the virtual optical power profile can be described as having a base power at the lens center O, and in the near zone, a positive constant power is added to the aspheric reference power to form a virtual optical power profile that may also be considered as a power profile of a virtual aspheric lens. In other words, the near zone has a base power at the lens center O, and a positive constant power is added to the aspheric reference power between a predetermined radial range of the virtual aspheric lens. The virtual optical power profile in the near zone is preferably such that the positive vertical spherical aberration of the human cornea, particularly the average human cornea, is compensated for. This compensation can be partial or complete. Thus, in one embodiment, the near zone has a predetermined base power at the lens center O, and a positive constant power is added to the aspheric base power over a predetermined radial range of the virtual aspheric lens to fully compensate for the positive vertical spherical aberration of the average human cornea. Thus, the third aspect is: The lens has a lens center O as a concentric region, and the lens includes the lens center O and corrects vision for distance vision. The lens also has a near region that is positioned outside the far region when viewed radially outward from the lens center O and corrects vision for near vision. The lens also has an outer region that is positioned outside the near region and corrects vision for distance vision. the outer region is reduced in power to provide a negative longitudinal spherical aberration that at least partially offsets the positive longitudinal spherical aberration caused by the cornea; In the near area, a positive constant power is added to an aspherical reference power within a predetermined radial range of a virtual aspherical lens having a predetermined base power at the lens center O and completely offsetting the positive vertical spherical aberration caused by the cornea, the near region comprises at least three radially aligned sub-regions; Subregion 1 provides a positive power deviation from the positive constant power, Sub-region 2 provides zero power deviation, in particular nearly zero power deviation, relative to the positive constant power, Sub-region 3 is an intraocular lens that provides a negative power deviation from the positive constant power. The power reduction of the aspheric power profile in the near zone is preferably equal to the power reduction in the outer zone, in other words, in one example, the optical power in the outer zone decreases with increasing radial distance to the lens center O in line with the reduction of the aspheric power profile of the virtual optical power profile in the near zone. Furthermore, preferably, the power decrease with increasing radial distance in the outer region is equal to the power decrease with increasing radial distance in the distance region. In particular, in the outer and distance regions, the optical power can decrease with increasing radial distance to the lens center O in line with the decrease in the aspheric power profile of the virtual optical power profile in the near region. In other words, in one example, the power decrease in the outer and distance regions can be represented by the aspheric power profile of the virtual optical power profile in the near region; i.e., in one example, the IOL comprises an aspheric power profile extending from the lens center O through the distance region, the near region, and the outer region, where a positive constant power is added to the aspheric power profile in the near region.

[0028] According to a fourth aspect of the present invention, there is provided a lens having at least one distance region for correcting vision for distance vision and at least one near region for correcting vision for near vision, the distance region and the near region being concentric with a lens center O, the near region comprises at least three radially aligned sub-regions; Sub-region 1 provides a positive power deviation to a virtual optical power profile in the near region, and the virtual optical power profile is an aspheric power profile to which a positive constant power is added; Subregion 2 provides zero power deviation with respect to the virtual optical power profile; An ophthalmic lens is provided in which sub-region 3 provides a negative power deviation relative to said virtual optical power profile. In other words, subregion 1 provides a positive power deviation for a positive constant power, subregion 2 provides a zero power deviation for a positive constant power, and subregion 3 provides a negative power deviation for a positive constant power. An ophthalmic lens having these three sub-zones in the near zone leads to an extended depth of focus for near vision. Preferably, the aspheric power profile (which may also be considered an aspheric reference power) of the virtual optical power profile can be described as having a base power at the lens center O, and in the near zone, a positive constant power is added to the aspheric reference power to form a virtual optical power profile that may also be considered a power profile of a virtual aspheric lens. In other words, in the near zone, a positive constant power is added to a reference power having a predetermined base power at the lens center O. Thus, the fourth aspect is: The lens has at least one distance area for correcting vision for distance vision and at least one near area for correcting vision for near vision, the distance area being concentric with the lens center O; In the near area, a positive constant power is added to a reference power having a predetermined base power at the lens center O, the near region comprises at least three radially aligned sub-regions; Subregion 1 provides a positive power deviation from the positive constant power, Sub-region 2 has zero power deviation from the positive constant power, in particular Abbreviation ze This results in deviation in the refractive power. Sub-area 3 is an ophthalmic lens that provides a negative power deviation relative to said positive constant power. Preferably, in subregion 2, the power deviation is considered to be zero when the average power deviation in subregion 2 is in the range of -0.2 to 0.2 D. For this reason, a power deviation of zero can also be considered to be a power deviation of approximately zero. In one example, also in the fourth embodiment, in the distance region, the optical power of the lens decreases, particularly decreases continuously, as the radial distance to the lens center O increases. The distance region in which the optical power of the lens decreases as the radial distance to the lens center O increases can also be considered a distance region in which the power decreases. In one example, in the distance region, the optical power of the lens decreases as the radial distance to the lens center O increases, i.e., the distance region decreases in power to at least partially offset the positive vertical spherical aberration of the human cornea with negative vertical spherical aberration. Thus, in one example, in the distance region, the decrease in optical power with increasing radial distance to the lens center, i.e., the corresponding power profile, is such that the positive vertical spherical aberration of the human cornea is at least partially offset. This allows for further improved distance vision. In one example, the power reduction of the aspheric power profile in the near zone is equal to the power reduction in the distance zone, i.e., in one example, the optical power decreases in the distance zone with increasing radial distance to the lens center in line with the reduction of the aspheric power profile of the virtual optical power profile in the near zone.

[0029] The fifth aspect is With respect to the area of ​​the near region, The area ratio of the sub-region 1 is 15 to 50%, The area ratio of the sub-region 2 is 30 to 70%; In the intraocular lens according to any one of the first to fourth aspects, the area ratio of the sub-regions 3 is 15 to 50%.

[0030] The sixth aspect is The average value of the positive power deviation in the sub-region 1 is 0.3 to 1D, The average value of the approximately zero power deviation in the subregion 2 is −0.2 to 0.2D, In the subregion 3 Note The intraocular lens according to any one of the first to fifth aspects, wherein the average value of the negative power deviation is −0.3D or less.

[0031] A seventh aspect is The intraocular lens according to any one of the first to sixth aspects, wherein the positive fixed power is 1 to 4D.

[0032] The eighth aspect is The intraocular lens according to any one of the first to seventh aspects, wherein the sub-regions 1 to 3 are arranged in one of the following orders when viewed in the radial direction from the lens center O. ·Sub area 1, sub area 2, sub area 3 ·Sub area 1, sub area 3, sub area 2 ·Sub area 2, sub area 1, sub area 3 ·Sub area 2, sub area 3, sub area 1 ·Sub area 3, sub area 1, sub area 2 ·Sub area 3, sub area 2, sub area 1

[0033] A ninth aspect is With respect to the area of ​​the near region, The area ratio of the sub-region 1 is 15 to 50%, The area ratio of the sub-region 2 is 30 to 70%; The ophthalmic lens according to any one of the first to eighth aspects, wherein the area ratio of the sub-regions 3 is 15 to 50%.

[0034] A tenth aspect is The average value of the positive power deviation in the sub-region 1 is 0.3 to 1D, The average value of the approximately zero power deviation in the subregion 2 is −0.2 to 0.2D, In the subregion 3 Note The ophthalmic lens according to any one of the first to ninth aspects, wherein the average value of the negative power deviation is −0.3D or less.

[0035] An eleventh aspect is The ophthalmic lens according to any one of the first to tenth aspects, wherein the positive fixed power is 1 to 4D.

[0036] A twelfth aspect is The ophthalmic lens according to any one of the first to eleventh aspects, wherein the sub-regions 1 to 3 are arranged in one of the following orders when viewed in the radial direction from the lens center O. ·Sub area 1, sub area 2, sub area 3 ·Sub area 1, sub area 3, sub area 2 ·Sub area 2, sub area 1, sub area 3 ·Sub area 2, sub area 3, sub area 1 ·Sub area 3, sub area 1, sub area 2 ·Sub area 3, sub area 2, sub area 1

[0037] According to a 13th aspect of the present invention, there is provided an intraocular lens according to any one of the first to 12th aspects, wherein the optical power changes continuously, discontinuously, or with a power jump at at least one of the boundary between two sub-regions of the near region and the boundary between the near region and the far region when the near region and the far region are adjacent to each other. Thus, there are several boundaries, namely boundaries between different sub-regions of the near region and at least one boundary between the near region and the far region when the near region and the far region are adjacent, and at least some of these boundaries the change in power is continuous, discontinuous or a power jump. The power jump is preferably defined as the vertical change in a graph showing the optical power as a function of the radial distance to the lens center O. This vertical change can be defined as ∞D / mm. The change in optical power is preferably considered discontinuous when the change in power is abrupt, i.e., greater than a predetermined power change threshold.Preferably, the predetermined power change threshold is 100D / mm.Therefore, preferably, if the power change at the boundary is 100D / mm or more, it is considered to be abrupt, and therefore discontinuous.If the power change is not discontinuous, it is considered to be continuous. Thus, the optical power change at each boundary can also be defined as a) abrupt, b) a power jump, or c) neither abrupt nor a power jump. In one example, abrupt power changes can also be considered abrupt power changes. In one embodiment, an intraocular lens according to any one of aspects 1 to 12 may be provided, in which the power changes smoothly or suddenly, or there is a power jump, at at least one of the boundaries between two different sub-regions, and the boundaries between each of sub-regions 1 to 3 and the far region when the near region and the far region are adjacent to each other. The power variation can be considered smooth if the curve representing the power dependence on the radial distance to the lens center O is differentiable, in other words, if there are no "corners" in the curve.

[0038] According to a 14th aspect of the present invention, there is provided an ophthalmic lens according to any one of the first to 13th aspects, wherein the optical power changes continuously, discontinuously, or with a power jump at at least one of the boundary between two sub-regions of the near region and the boundary between the near region and the far region when the near region and the far region are adjacent to each other. Thus, there are several boundaries, namely boundaries between different sub-regions of the near region and at least one boundary between the near region and the far region when the near region and the far region are adjacent, and at least some of these boundaries the change in power is continuous, discontinuous or a power jump. As mentioned above, the power jump is preferably defined as the vertical change in a graph showing the optical power as a function of the radial distance to the lens center O. This vertical change can be defined as ∞D / mm. As also mentioned above, the change in optical power is preferably considered discontinuous when the change in power is abrupt, i.e., greater than a predetermined power change threshold.Preferably, the predetermined power change threshold is 100D / mm.Therefore, preferably, if the power change at the boundary is 100D / mm or more, it is considered to be abrupt, and therefore discontinuous.If the power change is not discontinuous, it is considered to be continuous. Thus, the optical power change at each boundary can also be defined as a) abrupt, b) a power jump, or c) neither abrupt nor a power jump. In one example, abrupt power changes can also be considered abrupt power changes. In one embodiment, an ophthalmic lens according to any one of aspects 1 to 13 may be provided, in which the power changes smoothly or suddenly, or there is a power jump, at at least one of the boundaries between two different sub-regions, and the boundaries between the far region and each of sub-regions 1 to 3 when the near region and the far region are adjacent to each other. As explained above, the power variation can be considered smooth if the curve representing the power dependence on the radial distance to the lens center O is differentiable, in other words, if there are no "corners" in the curve.

[0039] A fifteenth aspect is The intraocular lens according to any one of the first to fourteenth aspects, wherein the diameter of the near region in plan view is 1.2 to 2.5 mm. Thus, the diameter of the proximal region, i.e., the radial or diametric expansion of the proximal region, will be in the range of 1.2 to 2.5 mm.

[0040] A sixteenth aspect is An intraocular lens according to any one of aspects 1 to 15, wherein the change in power is continuous or discontinuous, or the power jumps, at at least one of the boundaries between different sub-regions within the near region, the boundary between any of sub-regions 1 to 3 and the far region when the near region and the far region are adjacent, and the boundary between any of sub-regions 1 to 3 and the far region when the near region and the outer region are adjacent.

[0041] A seventeenth aspect is The intraocular lens according to any one of the first to sixteenth aspects, wherein the inner diameter of the near region in plan view is 1.4 to 2.2 mm and the outer diameter is 2.6 to 3.5 mm. Therefore, the inner diameter of the near distance region, i.e., the radial distance between the inner diameter and the lens center O, can be in the range of 1.4 to 2.2 mm. The outer diameter of the near distance region, i.e., the radial distance between the outer diameter and the lens center O, can be in the range of 2.6 to 3.5 mm.

[0042] The eighteenth aspect is the ophthalmic lens is a phakic intraocular lens; the near zone includes a lens center O; the far region is disposed outside the near region when viewed radially outward from a lens center O, The ophthalmic lens according to any one of the first to seventeenth aspects, wherein the diameter of the near region in plan view is 1.4 to 3 mm. Thus, the diameter of the proximal region, ie the radial or diametric expansion of the proximal region, may be in the range of 1.4 to 3 mm, in particular 1.4 to 3.0 mm.

[0043] A nineteenth aspect is the ophthalmic lens is a phakic intraocular lens; the far region includes the lens center O; the near area is disposed outside the far area when the radial direction is taken outward from the lens center O, an outer region disposed outside the near region and correcting vision for distance vision; The ophthalmic lens according to any one of the first to eighteenth aspects, wherein the inner diameter of the near region in plan view is 1.6 to 2.4 mm and the outer diameter is 2.9 to 3.6 mm. Therefore, the inner diameter of the near distance region, i.e., the radial distance between the inner diameter and the lens center O, can be in the range of 1.6 to 2.4 mm. The outer diameter of the near distance region, i.e., the radial distance between the outer diameter and the lens center O, can be in the range of 2.9 to 3.6 mm.

[0044] The twentieth aspect is the ophthalmic lens is a contact lens; the near zone includes a lens center O; the far region is disposed outside the near region when viewed radially outward from a lens center O, The ophthalmic lens according to any one of the first to nineteenth aspects, wherein the diameter of the near region in plan view is 1.4 to 3 mm. Thus, the diameter of the proximal region, ie the radial or diametric expansion of the proximal region, may be in the range of 1.4 to 3 mm, in particular 1.4 to 3.0 mm.

[0045] A twenty-first aspect is the ophthalmic lens is a contact lens; the far region includes the lens center O; the near area is disposed outside the far area when the radial direction is taken outward from the lens center O, an outer region disposed outside the near region and correcting vision for distance vision; The ophthalmic lens according to any one of the first to twentieth aspects, wherein the inner diameter of the near region in plan view is 1.6 to 2.4 mm, and the outer diameter is 2.9 to 3.6 mm. Therefore, the inner diameter of the near zone, i.e., the radial distance between the inner diameter and the lens center O, can be in the range of 1.6 to 2.4 mm. The outer diameter of the near zone, i.e., the radial distance between the outer diameter and the lens center O, can be in the range of 2.9 to 3.6 mm.

[0046] According to a 22nd aspect of the present invention, there is provided the intraocular lens according to any one of the 1st to 21st aspects, wherein the intraocular lens is a toric lens. In a preferred embodiment of any of the above aspects, in the first sub-region, the optical power decreases as the radial distance to the lens center O increases. Furthermore, preferably, the decrease in the first sub-region is concave, i.e. follows a concave curve. In the third sub-region, preferably, the optical power decreases as the radial distance to the lens center O increases. Furthermore, preferably, the decrease in the third sub-region is convex, i.e. follows a convex curve. It is also preferred that the third sub-region comprises several, in particular two, sub-sub-regions, in which, in each sub-sub-region, the optical power decreases as the radial distance to the lens center O increases. In one example, in each sub-sub-region, the decrease is convex, i.e. follows a convex curve. The previous paragraph preferably applies to intraocular and / or ophthalmic lenses. It has been found that intraocular or ophthalmic lenses having these sub-zones in the near zone can lead to a further extension of the depth of focus for near vision. Preferably, a power profile or power curve is considered concave (specifically, concave in the negative direction of the power profile's vertical axis) if it points to the right (i.e., the power profile curves clockwise from 12 o'clock to 3 o'clock when the vertical axis is power and the horizontal axis is radial distance) as you move along the power profile or power curve away from the lens center O. Preferably, a power profile or power curve is considered convex (specifically, convex in the negative direction of the power profile's vertical axis) if it points to the left (i.e., the power profile curves counterclockwise from 9 o'clock to 6 o'clock when the vertical axis is power and the horizontal axis is radial distance) as you move along the power profile or power curve away from the lens center O. Hereinafter, when the vertical axis represents power and the horizontal axis represents radial distance, the concavities and convexities in the power profile will be defined in the same way as above.

[0047] According to a 23rd aspect of the present invention, there is provided a method for optically designing an intraocular lens according to any one of the first to 22nd aspects. In one example, the optical design method comprises: Designing an aspheric power profile having an optical power that decreases as the distance to the center O of the lens to be designed increases; adding a positive constant power to a region of the designed aspheric power profile to design a near zone, wherein at least a portion of the designed aspheric power profile outside the near zone forms a far zone; and a step of changing the optical power in the near region to design at least three sub-regions, wherein in sub-region 1, the power is increased to design a positive power deviation for the designed aspheric power profile to which the positive fixed power has been added, in sub-region 2, the power is not changed to design a zero power deviation for the designed aspheric power profile to which the positive fixed power has been added, and in sub-region 3, the power is decreased to design a negative power deviation for the designed aspheric power profile to which the positive fixed power has been added. Preferably, the aspheric power profile is designed to provide a negative longitudinal spherical aberration that at least partially offsets the positive longitudinal spherical aberration of the human cornea, particularly the average human cornea.

[0048] A twenty-fourth aspect is A method for manufacturing an intraocular lens, in which an intraocular lens designed by the optical design method for an intraocular lens according to the 23rd aspect is manufactured by at least one of lathing, molding, and 3D printing.

[0049] The 25th aspect is The ophthalmic lens according to any one of the first to twenty-second aspects, wherein the ophthalmic lens is a toric lens.

[0050] According to a 26th aspect of the present invention, there is provided a method for optically designing an ophthalmic lens according to any one of the first to twenty-second aspects. In one example, the optical design method comprises: - designing an aspheric power profile having an optical power that decreases as the distance to the center O of the lens to be designed increases; - adding a positive constant power to a region of the designed aspherical power profile to design a near zone, wherein at least a portion of the designed aspherical power profile outside the near zone forms a far zone; - changing the optical power in the near zone to design at least three subzones, wherein in subzone 1, the power is increased to design a positive power deviation for the designed aspheric power profile to which the positive constant power has been added, in subzone 2, the power is not changed to design a zero power deviation for the designed aspheric power profile to which the positive constant power has been added, and in subzone 3, the power is decreased to design a negative power deviation for the designed aspheric power profile to which the positive constant power has been added; Includes. Preferably, the aspheric power profile is designed to provide a negative longitudinal spherical aberration that at least partially offsets the positive longitudinal spherical aberration of the human cornea, particularly the average human cornea.

[0051] A twenty-seventh aspect is A method for manufacturing an ophthalmic lens, comprising manufacturing an ophthalmic lens designed by the optical design method for an ophthalmic lens according to the twenty-sixth aspect by at least one of lathing, molding, and 3D printing. [Effects of the Invention]

[0052] According to the present invention, the depth of focus for near vision and / or intermediate vision can be increased and / or the image quality for far vision can be improved compared to the specific examples shown below to which the present invention is not applied (listed as "Flat"). [Brief explanation of the drawings]

[0053] [Figure 1A]FIG. 1 shows a prior art (referred to herein as "Flat") aspheric EDOF IOL. [Figure 1B] FIG. 1B is a diagram showing a power profile when the vertical axis (unit: D) ​​in FIG. 1A is changed to add power. [Figure 2] FIG. 1B is a diagram showing a power profile when the vertical axis (unit: D) ​​in FIG. 1A is changed to total power. [Figure 3A] FIG. 2 illustrates how a ray of light from an intermediate distance is focused onto the retina by the cornea and the EDOF of FIG. 1. [Figure 3B] FIG. 3B shows that the range of intermediate distances at which objects are clearly visible is wider than the range in FIG. 3A. [Figure 4] FIG. 1 is a diagram of a power profile of a two-zone EDOF (corresponding to the first embodiment). [Figure 5A] FIG. 2 is a diagram of a power profile of a two-zone EDOF (another example corresponding to the first embodiment). [Figure 5B] FIG. 5B is a diagram showing a power profile when the vertical axis (unit: D) ​​in FIG. 5A is changed to addition power. [Figure 5C] FIG. 10 is a diagram showing the power profile of a two-zone EDOF (yet another example corresponding to the first embodiment). [Figure 5D] FIG. 5D is a diagram showing a power profile when the vertical axis (unit: D) ​​in FIG. 5C is changed to addition power. [Figure 6A] FIG. 5B is a diagram showing the total power profile of a simulated eye model consisting of the cornea and EDOF shown in FIG. 5A. [Figure 6B] FIG. 5D is a diagram showing the total power profile of a simulated eye model consisting of the cornea and EDOF shown in FIG. 5C. [Figure 7] 10 shows yet another example of the first embodiment of the present invention. [Figure 8A] FIG. 10 is a diagram showing TFRs corresponding to a pupil diameter of 2 mm at a spatial frequency of 50 lp / mm (line pair / mm) of the simulated eye model using the EDOF shown in FIG. 1 (prior art) and FIG. 7 (embodiment 1). [Figure 8B] This is a diagram corresponding to FIG. 8A when the pupil diameter is 2.5 mm. [Figure 8C] This is a diagram corresponding to FIG. 8A when the pupil diameter is 3 mm. [Figure 8D] This is a diagram corresponding to FIG. 8A when the pupil diameter is 3.5 mm. [Figure 8E] This is a diagram corresponding to FIG. 8A when the pupil diameter is 4 mm. [Figure 9A] This is a diagram corresponding to FIG. 8A when the spatial frequency is 100 lp / mm. [Figure 9B] This is a diagram corresponding to FIG. 9A when the pupil diameter is 2.5 mm. [Figure 9C] This is a diagram corresponding to FIG. 9A when the pupil diameter is 3 mm. [Figure 9D] This is a diagram corresponding to FIG. 9A when the pupil diameter is 3.5 mm. [Figure 9E] This is a diagram corresponding to FIG. 9A when the pupil diameter is 4 mm. [Figure 10] FIG. 10 is a diagram showing the results of image simulation at each object distance when the pupil diameter is 2 mm. [Figure 11] This is a diagram corresponding to FIG. 10 when the pupil diameter is 3 mm. [Figure 12] This is a diagram corresponding to FIG. 10 when the pupil diameter is 4 mm. [Figure 13A] This is an MTF graph obtained by simulating a long distance of 6m and a pupil diameter of 3mm. [Figure 13B] This is a diagram corresponding to FIG. 13A in the case of a long distance of 12 m. [Figure 13C] This is a diagram corresponding to FIG. 13A in the case of a long distance of 25 m. [Figure 14A] This is an MTF graph obtained by simulating a long distance of 6m and a pupil diameter of 4mm. [Figure 14B] This is a diagram corresponding to FIG. 14A in the case of a long distance of 12 m. [Figure 14C] This is a diagram corresponding to FIG. 14A in the case of a long distance of 25 m. [Figure 15] FIG. 10 is a diagram showing the results of image simulation at each object distance when the pupil diameter is 2 mm. [Figure 16] This is a diagram corresponding to FIG. 15 when the pupil diameter is 3 mm. [Figure 17] This is a diagram corresponding to FIG. 15 when the pupil diameter is 4 mm. [Figure 18] FIG. 10 is a diagram showing the results of image simulation at each object distance when the pupil diameter is 2 mm. [Figure 19] This is a diagram corresponding to FIG. 18 when the pupil diameter is 3 mm. [Figure 20A] FIG. 1 shows the power profile of a prior art aspheric EM-IOL. [Figure 20B] FIG. 20B is a diagram corresponding to FIG. 20A in the case of an EM-IOL (corresponding to embodiment 2) according to the present invention. [Figure 21A] FIG. 20B is a diagram showing TFRs at a spatial frequency of 50 lp / mm (line pairs / mm) of a simulated eye model using the IOLs shown in FIG. 20A (prior art) and FIG. 20B (embodiment 2) according to a pupil diameter of 2.5 mm. [Figure 21B] This is a diagram corresponding to FIG. 21A when the pupil diameter is 3 mm. [Figure 21C] This is a diagram corresponding to FIG. 21A when the pupil diameter is 3.5 mm. [Figure 22A] This is a diagram corresponding to FIG. 21A when the spatial frequency is 100 lp / mm. [Figure 22B] This is a diagram corresponding to FIG. 22A when the pupil diameter is 3 mm. [Figure 22C] This is a diagram corresponding to FIG. 22A when the pupil diameter is 3.5 mm. [Figure 23A] FIG. 1 shows the power profile of a prior art multifocal lens. [Figure 23B] FIG. 23B is a diagram corresponding to FIG. 23A in the case of a multifocal lens according to the present invention (corresponding to the third embodiment). [Figure 24A] FIG. 23B is a diagram showing TFRs at a spatial frequency of 50 lp / mm (line pairs / mm) of a simulated eye model using the IOLs shown in FIG. 23A (prior art) and FIG. 23B (embodiment 3) according to a pupil diameter of 2.5 mm. [Figure 24B] This is a diagram corresponding to FIG. 24A when the pupil diameter is 3 mm. [Figure 24C] This is a diagram corresponding to FIG. 24A when the pupil diameter is 3.5 mm. [Figure 25A] This is a diagram corresponding to FIG. 24A when the spatial frequency is 100 lp / mm. [Figure 25B] This is a diagram corresponding to FIG. 25A when the pupil diameter is 3 mm. [Figure 25C] This is a diagram corresponding to FIG. 25A when the pupil diameter is 3.5 mm. [Figure 26A] FIG. 1 shows the power profile of a prior art three-zone EDOF. [Figure 26B] FIG. 26B is a diagram corresponding to FIG. 26A in the case of a three-zone EDOF according to the present invention (corresponding to embodiment 1′). [Figure 27A] FIG. 26B is a diagram showing TFRs at a spatial frequency of 50 lp / mm (line pairs / mm) of a simulated eye model using the IOLs shown in FIG. 26A (prior art) and FIG. 26B (embodiment 1′) according to a pupil diameter of 2 mm. [Figure 27B] This is a diagram corresponding to FIG. 27A when the pupil diameter is 2.5 mm. [Figure 27C] This is a diagram corresponding to FIG. 27A when the pupil diameter is 3 mm. [Figure 27D] This is a diagram corresponding to FIG. 27A when the pupil diameter is 3.5 mm. [Figure 27E] This is a diagram corresponding to FIG. 27A when the pupil diameter is 4 mm. [Figure 28A] FIG. 10 is a diagram showing MTF according to a pupil diameter of 2 mm near 0D (distance of far vision). [Figure 28B] This is a diagram corresponding to FIG. 28A when the pupil diameter is 2.5 mm. [Figure 28C] This is a diagram corresponding to FIG. 28A when the pupil diameter is 3 mm. [Figure 28D] This is a diagram corresponding to FIG. 28A when the pupil diameter is 3.5 mm. [Figure 28E] This is a diagram corresponding to FIG. 28A when the pupil diameter is 4 mm. [Figure 29A] FIG. 10 is a diagram showing the power profile of pattern c1. [Figure 29B] FIG. 10 is a diagram showing the power profile of pattern c2. [Figure 29C] FIG. 10 is a diagram showing the power profile of pattern c3d1. [Figure 29D] FIG. 29B is a diagram that combines the patterns of FIGS. 29A to 29C into one. [Figure 30A] FIG. 29B is a diagram showing TFRs at a spatial frequency of 50 lp / mm (line pairs / mm) in simulated eye models using the IOLs shown in FIGS. 29A to 29C, and corresponding to a pupil diameter of 2.5 mm. [Figure 30B] This is a diagram corresponding to FIG. 30A when the pupil diameter is 3 mm. [Figure 30C] This is a diagram corresponding to FIG. 30A when the pupil diameter is 3.5 mm. [Figure 31A] FIG. 10 is a diagram showing the power profile of pattern b1. [Figure 31B] FIG. 10 is a diagram showing the power profile of pattern b2. [Figure 31C] FIG. 10 is a diagram showing the power profile of pattern b3. [Figure 31D] FIG. 31B is a diagram in which the patterns of FIGS. 31A to 31C are combined into one. [Figure 32A] FIG. 31B is a diagram showing TFRs at a spatial frequency of 50 lp / mm (line pairs / mm) in simulated eye models using the IOLs shown in FIGS. 31A to 31C, and corresponding to a pupil diameter of 2.5 mm. [Figure 32B] This is a diagram corresponding to FIG. 32A when the pupil diameter is 3 mm. [Figure 32C] This is a diagram corresponding to FIG. 32A when the pupil diameter is 3.5 mm. [Figure 33A] FIG. 10 is a diagram showing the power profile of pattern a1c1. [Figure 33B] FIG. 10 is a diagram showing the power profile of pattern a1c2. [Figure 33C] FIG. 10 is a diagram showing the power profile of pattern a2c1. [Figure 33D]FIG. 10 is a diagram showing the power profile of pattern a2c2. [Figure 33E] This is a diagram that combines the patterns of FIGS. 33A to 33D into one. [Figure 34A] FIG. 33B is a diagram showing TFRs at a spatial frequency of 50 lp / mm (line pairs / mm) in simulated eye models using the IOLs shown in FIGS. 33A to 33D, and corresponding to a pupil diameter of 2.5 mm. [Figure 34B] This is a diagram corresponding to FIG. 34A when the pupil diameter is 3 mm. [Figure 34C] This is a diagram corresponding to FIG. 34A when the pupil diameter is 3.5 mm. [Figure 35A] FIG. 1 shows the power profile of an IOL without a power jump. [Figure 35B] FIG. 1 shows the power profile of a Power Jump IOL. [Figure 35C] FIG. 35B is a diagram that combines the patterns of FIGS. 35A and 35B. [Figure 36A] FIG. 35C is a diagram showing TFRs at a spatial frequency of 50 lp / mm (line pairs / mm) in simulated eye models using the IOLs shown in FIGS. 35A and 35B, and corresponding to a pupil diameter of 2.5 mm. [Figure 36B] This is a diagram corresponding to FIG. 36A when the pupil diameter is 3 mm. [Figure 36C] This is a diagram corresponding to FIG. 36A when the pupil diameter is 3.5 mm. [Figure 37A] FIG. 1 shows the power profile of a prior art Flat. [Figure 37B] FIG. 10 is a diagram showing the power profile of CenterFlat. [Figure 37C] FIG. 10 is a diagram showing the power profile of MiddleFlat. [Figure 37D] FIG. 10 is a diagram showing the power profile of OuterFlat. [Figure 37E] This is a diagram that combines the patterns of FIGS. 37A to 37D into one. [Figure 38A]FIG. 37B is a diagram showing TFRs at a spatial frequency of 50 lp / mm (line pairs / mm) in simulated eye models using the IOLs shown in FIGS. 37A to 37D, and corresponding to a pupil diameter of 2.5 mm. [Figure 38B] This is a diagram corresponding to FIG. 38A when the pupil diameter is 3 mm. [Figure 38C] This is a diagram corresponding to FIG. 38A when the pupil diameter is 3.5 mm. [Figure 39A] FIG. 10 is a diagram showing the power profile of OuterHigher a1c1. [Figure 39B] FIG. 10 is a diagram showing the power profile of OuterHigher a2c2. [Figure 39C] FIG. 39B is a diagram that combines the patterns of FIGS. 39A and 39B. [Figure 40A] FIG. 39C is a diagram showing TFRs in response to a pupil diameter of 2 mm at a spatial frequency of 50 lp / mm (line pairs / mm) in a simulated eye model using each of the IOLs shown in FIGS. 39A and 39B. [Figure 40B] This is a diagram corresponding to FIG. 40A when the pupil diameter is 2.5 mm. [Figure 40C] This is a diagram corresponding to FIG. 40A when the pupil diameter is 3 mm. [Figure 40D] This is a diagram corresponding to FIG. 40A when the pupil diameter is 3.5 mm. [Figure 41A] FIG. 1 is a diagram showing a power profile of a two-zone type according to the prior art. [Figure 41B] FIG. 10 is a diagram showing an example power profile of a two-zone type corresponding to [Mode Group 2]. [Figure 42A] FIG. 1 is a diagram showing a three-zone type power profile of the prior art. [Figure 42B] FIG. 10 is a diagram showing an example power profile of a three-zone type corresponding to [Mode Group 2]. [Figure 43] FIG. 10 is a diagram showing many further variations obtained by extending the modified example according to the fourth embodiment to [mode group 2]. DETAILED DESCRIPTION OF THE INVENTION

[0054] For configurations not described below, known configurations may be appropriately adopted. In particular, the contents (especially the support portion) described in a document (WO2009 / 153873) disclosed by the present inventor may be applied to this embodiment. In this specification, the symbol "to" indicates a value greater than or equal to a predetermined value and less than or equal to a predetermined value. In particular, an expression such as "A to B" indicates a range from A to B. Furthermore, the lens body of the intraocular lens discussed in this specification has two opposing surfaces. The surface of the lens body that comes into contact with the posterior capsule when the intraocular lens is inserted into the lens capsule can be referred to as the posterior surface, the retina-side surface, or the retina-side surface in the optical axis direction, but the term "posterior surface" will be used primarily in this specification. The other surface can be referred to as the anterior surface, the cornea-side surface, or the cornea-side surface in the optical axis direction, but the term "anterior surface" will be used primarily in this specification. The optical axis direction is also the lens thickness direction, and is the direction from the posterior surface to the anterior surface or the reverse direction. The optical axis direction is the z-axis direction. Viewing the intraocular lens in the z-axis direction is referred to as the "planar view," and unless otherwise specified, this planar view will be described.

[0055] The outline of this embodiment is as follows. As this embodiment, a two-zone EDOF is mainly exemplified (Embodiment 1). In this specification, two zones refers to the fact that the area that exhibits the lens function to achieve the wearer's prescription values ​​is composed of one area (zone) that corrects near vision and includes the lens center O, and one area (zone) that corrects far vision. Similar to this two-zone EDOF, a two-zone EM-IOL is also illustrated (Embodiment 2). Similar to this two-zone EDOF, a two-zone multifocal lens is also exemplified (Embodiment 3). In addition to this two-zone EDOF, a three-zone EDOF is also exemplified (Embodiment 1'). A three-zone EDOF refers to a configuration consisting of one area (zone) for correcting distance vision that includes the lens center O, one area (zone) for correcting near vision, and another area (zone) outside of that for correcting distance vision. Although not exemplified in this specification, a three-zone EM-IOL (embodiment 2') and a three-zone multifocal lens (embodiment 3') are also included within the technical scope of the present invention. Furthermore, various modified examples relating to the behavior of the power profile in the near area for correcting near vision are also illustrated (Fourth Embodiment). The invention relating to the intraocular lens including each of the above embodiments is referred to as [Aspect Group 1] in this specification.

[0056] [Mode Group 2] differs from [Mode Group 1] in that it exemplifies a phakic intraocular lens or an implantable contact lens rather than a general intraocular lens.

[0057] The content common to each embodiment will be explained at the beginning as a "common embodiment."

[0058] The first aspect of the present invention in [Means for Solving the Problems of the Present Invention] corresponds to [Aspect Group 1]. The second aspect of the present invention in [Means for Solving the Problems of the Invention] corresponds to the first to third embodiments in [Aspect Group 1]. The third aspect of the present invention in [Means for Solving the Problems of the Present Invention] corresponds to embodiments 1' to 3' in [Aspect Group 1]. The fourth aspect of the present invention in [Means for Solving the Problems of the Invention] corresponds to [Aspect Group 2]. Literally, the fourth aspect includes not only [Aspect Group 2] but also [Aspect Group 1], but the fourth aspect in this specification mainly envisions [Aspect Group 2].

[0059] [Common embodiment] The following describes common aspects and inventive concepts common to the first and subsequent embodiments. Here, an intraocular lens belonging to [Aspect Group 1] will be exemplified.

[0060] The intraocular lens of the common embodiment (and other aspects described in this specification) comprises a lens body having a lens function and a support portion that supports the lens body within the lens capsule, similar to intraocular lenses of the prior art ("Flat" in the specific examples below, and the same applies hereinafter).

[0061] In a common embodiment, the intraocular lens is defined by the refractive power (power, dioptric power) relative to the radial distance from the lens center O. In this specification, the "direction radially away from the lens center O" is defined as the "outside."

[0062] There are no limitations on the material of the intraocular lens, and it may be made of at least one of silicone, hydrophobic acrylic resin, hydrophilic acrylic resin, hydrogel, PMMA, PMMA copolymer, and copolymer of HEMA (hydroxyethyl methacrylate) containing collagen (e.g., Collamer (registered trademark)).

[0063] In the common embodiment (and other aspects described herein), the entire lens body is exemplified as an optical part having a lens function. The "lens function" here refers to the lens function described above in the outline of this embodiment, which is the function of refracting incident light beams onto the retina.

[0064] In the first to third embodiments of the first aspect group, the entire lens body is illustrated as comprising one distance zone for correcting vision for distance vision and one near zone for correcting vision for near vision. However, the present invention is not limited to this example. For example, the intraocular lens may be a three-zone intraocular lens, as in the first to third embodiments described below. Furthermore, an intermediate zone may be provided between the distance zone and the near zone, surrounding the side zone (the distance zone or the near zone) closer to the center of the lens, or an additional zone may be provided radially outwardly surrounding the distance zone or the near zone. Two or more distance zones and / or two or more near zones may also be provided. However, the power may change continuously or discontinuously, or the power may jump, between each zone and / or between the sub-zones described below.

[0065] As the name suggests, "discontinuous change in power" refers to a situation where, in the graph of Figure 2, the change in power as you move away from the lens center O is actually discontinuous, and when the graph is converted into a function, the change in power as you move away from the lens center O is continuous but steep, meaning that the change in power is essentially discontinuous. Conversely, "continuous change in power" refers to a situation that does not fall under the category of "discontinuous change in power."

[0066] Regarding whether or not something is "steep," for example, a power change is considered steep when it has a rate of change of 100 D / mm or more. In other words, even if the power increases discontinuously for every 0.01 mm from a point a certain distance away from the lens center O, it is considered steep if it has a rate of change of 100 D / mm or more between that point and 0.05 mm. As the name suggests, a "power jump" refers to a state in which the power change is more than steep (in the power profile, the power change is vertical and the power change is ∞ D / mm).

[0067] In a plan view, the inner region (near region in embodiments 1 to 3) including the lens center O is circular, and the outer region (far region in embodiments 1 to 3) surrounding the near region is toric. In embodiments 1' to 3', the circular region including the lens center O is the far region, and the toric region surrounding the far region is the near region. In other aspects described in this specification, the intermediate region is a small toric region, and the additional region is a large toric region. Note that instead of a circular and / or toric shape, the intermediate region may be an elliptical and / or an elliptical toric shape.

[0068] 1A shows a power profile for a specific example described herein to which the present invention is not applied (described as "Flat," hereinafter also referred to simply as "Flat"), with the horizontal axis representing the position when viewed radially from the lens center O (unit: mm) and the vertical axis representing the power (unit: D). Hereinafter, unless otherwise specified, this type of power profile will be discussed. Specific straight lines and / or curves on the power profile are also referred to as graphs. FIG. 1B shows a power profile obtained by changing the vertical axis (unit: D) ​​in FIG. 1A to add power. FIG. 2 shows a power profile when the vertical axis (unit: D) ​​in FIG. 1A is changed to total power.

[0069] The distance from the lens center O is also called the radius. The solid line is the power profile of an intraocular lens according to a common embodiment (and other aspects described herein). The dashed line represents the power profile of a hypothetical aspherical lens that has a base power at the lens center O and completely cancels out the positive vertical spherical aberration caused by the cornea, that is, the hypothetical optical power profile. This power profile is also referred to as the aspherical reference power profile W. The aspherical reference power profile is also simply referred to as the aspherical power profile.

[0070] The cornea has positive refractive power. Spherical aberration increases as you move away from the center of the cornea. In other words, the dashed-dotted line representing the aspherical reference power profile W is a graph of a hypothetical aspherical lens that theoretically cancels out all of the positive vertical spherical aberration (axial aberration in the depth direction of the optical axis) caused by the cornea. Hereinafter, the meanings of the various lines will be the same.

[0071] An aspheric optical design IOL (aspheric IOL) with an aspheric reference power profile W is designed to correct or reduce all or part of the corneal spherical aberration. The degree to which the corneal spherical aberration is reduced varies for each IOL manufactured by each company. Each company's IOL is designed to reduce the corneal spherical aberration by a specific amount (value). In the optical design of the aspheric IOL, a corneal model having a spherical aberration value equal to the specific amount of spherical aberration to be reduced is preset, and the specific amount of spherical aberration to be reduced by the aspheric IOL is determined by selecting the optical parameters of the corneal model. During the optical design process, the total spherical aberration of the optical system (optical system) consisting of the predetermined corneal model and the designed aspheric IOL is zero (i.e., there is no spherical aberration).

[0072] The spherical aberration value of the given corneal model is determined as follows: The spherical aberration value of the given corneal model used in the optical design of the aspheric IOL is assumed to be the same as the mean spherical aberration value for a population of eye patients wearing the IOL, or the spherical aberration value of the given corneal model is determined by setting the spherical aberration value to a value that partially reduces the corneal spherical aberration of the population of eye patients.

[0073] The aspheric reference power profile W is the power distribution of an aspheric IOL. This power distribution has the power distribution characteristic of being able to completely or partially reduce the spherical aberration of the average cornea (statistical corneal optical parameters) of a population of aphakic patients. In this specification, the spherical aberration value of a predetermined corneal model is set to 0.27 μm. The dashed line in FIG. 1A is also an example of the power distribution of an aspheric IOL that can completely reduce the spherical aberration of a corneal model with a spherical aberration value of 0.27 μm. 0.27 μm may also be expressed as +0.27 μm. Furthermore, the present invention is not strictly limited to 0.27 μm, and may be, for example, a value in the range of +0.24 to +0.30 μm.

[0074] The near zone in this specification corrects visual acuity when viewing an object at one intermediate vision distance or one near vision distance. The near zone has a power obtained by adding one positive fixed power to an aspherical reference power within a predetermined range in the radial direction of a virtual aspherical lens that has a base power at the lens center O and completely offsets the positive vertical spherical aberration caused by the cornea. This "one positive fixed power" corresponds to the add power described above in this specification.

[0075] In this specification, the aspherical reference power profile W is also referred to as a reference base power profile (RBPP).The aspherical reference power profile W to which an add power is added is also referred to as a reference add power profile (RAPP).

[0076] As shown in Figure 1A, the power graph in the state where a single positive constant power is added in the near area has a shape obtained by shifting the graph of the aspherical reference power upward by the same constant power. Before the existence of sub-areas 1 to 3 described below, it is preferable that the power continuously decreases in the radial direction in the power graph in the state where a single positive constant power is added in the near area.

[0077] The positive fixed power may be 1 to 4D (particularly 1.0 to 4.0D).

[0078] In each group of embodiments, one positive fixed power is added, and then in a predetermined radial range within the near region (subregion 1 described below), a further power is added to the added state. In other words, even if "one positive fixed power is added," the final intraocular lens (or ophthalmic lens) in this specification does not have "one" positive fixed power added.

[0079] [Aspect Group 1] [Mode Group 1] will be described below. First, the concept of the present invention will be described with reference to Embodiment 1 (see FIG. 4 below). For details not described in Embodiment 2 and subsequent embodiments, please refer to the description of Embodiment 1.

[0080] <Embodiment 1> In embodiment 1, the near zone including the lens center O comprises at least three sub-zones arranged radially, Subregion 1 provides a positive power deviation from the positive constant power, Subregion 2 provides approximately zero power deviation from the positive constant power; Subregion 3 provides a negative power deviation from the positive constant power.

[0081] In other words, the concept of the present invention is to radially divide a near zone to which a single positive fixed power has been added into multiple zones, as shown in Figure 4. The zones are divided into a state in which power has been further added (a in Figure 4), a state in which power has been reduced (c and d in Figure 4), and a state in which there is almost no change (b in Figure 4). As a result, as shown in the specific examples below, it is possible to widen the depth of focus for near vision and / or intermediate vision and / or improve image quality for distance vision. The mechanism behind this will be explained later.

[0082] The "state in which further power is added" in sub-region 1 (a in FIG. 4) is a state in which a positive power deviation is brought about relative to the positive fixed power. As a specific example, the average value of the positive power deviation in sub-region 1 is 0.3 to 1 D (particularly 0.3 to 1.0 D). This average value is the difference value obtained by subtracting the positive fixed power from the power in sub-region 1, and averaging the difference value within sub-region 1 (for example, the average value of the difference value for each measurement point or each radial position). Hereinafter, unless otherwise specified, the average power deviation will be a value obtained in the same way.

[0083] The "state of almost no or no change (b in FIG. 4)" in subregion 2 includes the "state of slight change," and is therefore referred to as "resulting in approximately zero power deviation" (because something that is zero cannot be achieved, but something that is present can). As a specific example, the average value of the approximately zero power deviation in subregion 2 is -0.2 to 0.2D. This average value is the difference value obtained by subtracting the positive constant power from the power in subregion 2, and averaging it within subregion 2 (for example, the average value of the difference value for each measurement point or each radial position). In English, this is written as ZAPD (Zero Addition Power Deviation), omitting the "approximately" part, but the meaning remains the same as above.

[0084] The "state where the power has been reduced" in subregion 3 (c, d in FIG. 4) is a state where a negative power deviation occurs relative to a positive fixed power. As a specific example, the average value of the negative power deviation in subregion 3 is -0.3D or less. This average value is the difference (negative value) obtained by subtracting the positive fixed power from the power in subregion 3, and is averaged within subregion 3 (also a negative value, for example, the average value of the difference value for each measurement point or each radial position). As shown in c and d in FIG. 4, subregion 3 may be divided into multiple regions with different power profile shapes in the radial direction. The power may be reduced in multiple stages in the radial direction. Similarly, subregions 1 and 2 may also be divided into multiple regions with different power profile shapes in the radial direction.

[0085] The near region may also include subregions other than subregions 1 to 3. For example, subregions 1, 2, and 3 may be arranged in a row starting from the side closest to the lens center O, and subregion 4 (a region with the same function as subregion 2) that provides approximately zero power deviation may be provided separately outside subregion 3. This does not exclude the possibility of dividing a region with the same function and arranging it as a separate subregion. Furthermore, subregions 1 to 3 are not limited to being physically adjacent to each other. For example, subregions 2 and 1 may be arranged in a row starting from the side closest to the lens center O, followed by subregion 4, and then subregion 3 may be arranged outside of that. In this way, the expression "comprising at least three subregions arranged radially" encompasses both cases where subregions 1, 2, and 3 are physically adjacent to each other and cases where they are not adjacent to each other.

[0086] There is no limitation on the order of the sub-regions 1 to 3 when viewed in the radial direction from the lens center O (in FIG. 4, the sub-regions are described in the order of 1, 2, 3). For example, the order of arrangement of the sub-regions 1 to 3 when viewed in the radial direction from the lens center O may be any of the following: ·Sub area 1, sub area 2, sub area 3 ·Sub area 1, sub area 3, sub area 2 ·Sub area 2, sub area 1, sub area 3 ·Sub area 2, sub area 3, sub area 1 ·Sub area 3, sub area 1, sub area 2 ·Sub area 3, sub area 2, sub area 1 In this specification, the positive power deviation caused by sub-region 1 is also referred to as PAPD (Positive Addition Power Deviation), the approximately zero power deviation caused by sub-region 2 is also referred to as ZAPD (Zero Addition Power Deviation), and the negative power deviation caused by sub-region 3 is also referred to as NAPD (Negative Addition Power Deviation).

[0087] The shapes of sub-regions 1 to 3 in a plan view are, since they are arranged radially, toric, at least for the middle sub-region and the outermost sub-region when viewed radially from the lens center O. When the near region includes the lens center O, the innermost sub-region is circular, and when the near region does not include the lens center O, the innermost sub-region is also toric. The term "toric" here can be rephrased as "annular zone."

[0088] With respect to the area of ​​the near region, The area ratio of the sub-region 1 is 15 to 50%, The area ratio of the sub-region 2 is 30 to 70%; The area ratio of the sub-region 3 is preferably 15 to 50%. At least within this range, it has been demonstrated that the depth of focus for near vision and / or intermediate vision can be increased and / or the image quality for far vision can be improved, as will be shown in the specific examples below.

[0089] The lower limit of (the ratio of the area of ​​the sub-region 1) / (the ratio of the area of ​​the sub-region 3) may be 0.33 or 0.4, and the upper limit may be 3.3, 3.0, 2.5, 2.0, 1.5, or 1.3.

[0090] The power may change continuously or discontinuously, or may have a power jump, at least at the boundary between different sub-regions within the near region, and at the boundary between any of the sub-regions 1 to 3 and the far region when the near region and the far region are adjacent to each other. This variation is common to Embodiments 1 and 2 and [Aspect Group 2].

[0091] Variations of the sub-regions are detailed in the fourth embodiment below.

[0092] In the distance region of embodiment 1 (more specifically, [mode group 1]), the power is reduced so as to provide negative vertical spherical aberration that at least partially offsets the positive vertical spherical aberration caused by the cornea. Specifically, the power is reduced as the distance from the lens center O increases so as to offset at least a portion (preferably 70% or more, and more preferably all) of the positive vertical spherical aberration caused by the positive refractive power of the cornea. A specific example of complete offset is a power equal to the aspherical reference power (RBPP) of a virtual aspherical lens. In other words, the power in the distance region may be equal to the RBPP.

[0093] "A power equal to the aspherical reference power" means that the deviation from the aspherical reference power is less than ±0.30D (preferably less than ±0.15D) at a predetermined distance from the lens center O. The definition of "equal" with respect to power in this specification is the same as that in this paragraph. This "equal" is also referred to as "identical or similar." Alternatively, "a power equal to the aspherical reference power" may be considered as "a power with an average power deviation from the aspherical reference power of -0.2 to 0.2D."

[0094] In addition, "power obtained by adding one positive constant power to an aspherical reference power" indicates that the deviation from a graph in which one positive constant power is added to an aspherical reference power at a predetermined distance from the lens center O is less than ±0.30D (preferably less than ±0.15D). Alternatively, "power obtained by adding one positive constant power to an aspherical reference power" may be considered as "power in which the average value of the power deviation from a power obtained by adding one positive constant power to an aspherical reference power is -0.2 to 0.2D."

[0095] The above is the content of the first embodiment. Figures 4 to 19 correspond to the first embodiment. In the first subregion, i.e., the positive add power deviation region, the optical power can decrease. Furthermore, in the first subregion, the dependence of the optical power on the radial distance, i.e., the corresponding curve or function, can be concave, as exemplarily shown in Figures 5A, 5B, 5C, 6A, and 7. In the third subregion, i.e., the negative add power deviation region, the optical power can decrease. Furthermore, in the third subregion, the dependence of the optical power on the radial distance, i.e., the corresponding curve or function, can be convex, as exemplarily shown in Figures 5A, 5B, and 6A. The third subregion can also be further divided into subregions (ca, cb, in order from the closest to the lens center O) (reference numerals omitted in the following figures), such as the two subregions of the third subregion exemplarily shown in Figure 7. In each of these subregions exemplarily shown in Figure 7, the optical power can decrease. Each curve of each subregion can have its own convex curve or function, as exemplarily shown in Figure 7.

[0096] <Embodiment 2> The second embodiment is a two-zone EM-IOL in which the near zone includes the lens center O. FIGS. 20 to 22 correspond to the second embodiment. In this embodiment too, the optical power can decrease in the first subregion, i.e., the positive add power deviation region, and furthermore, in the first subregion, the dependence of the optical power on the radial distance, i.e., the corresponding curve or function, can be concave, as exemplarily shown in Figure 20B. In the third subregion, i.e., the negative add power deviation region, the optical power can decrease. Furthermore, in the third subregion, the dependence of the optical power on the radial distance, i.e., the corresponding curve or function, can be convex. The third subregion can also be further divided into sub-subregions, such as the two sub-subregions of the third subregion shown exemplarily in FIG. 20B. In each of these sub-subregions shown exemplarily in FIG. 20B, the optical power can decrease. Each curve in each sub-region can have its own convex curve or function, as also exemplarily shown in FIG. 20B.

[0097] <Embodiment 3> The third embodiment is a two-zone multifocal lens in which the near zone includes the lens center O. FIGS. 23 to 25 correspond to the third embodiment. In this embodiment too, the optical power can decrease in the first subregion, i.e., the positive add power deviation region, and furthermore, in the first subregion, the dependence of the optical power on the radial distance, i.e., the corresponding curve or function, can be concave, as exemplarily shown in Figure 23B. In the third subregion, i.e., the negative add power deviation region, the optical power can decrease. Furthermore, in the third subregion, the dependence of the optical power on the radial distance, i.e., the corresponding curve or function, can be convex. The third subregion can also be further divided into subregions, such as the two subregions of the third subregion shown exemplarily in FIG. 23B. In each of these subregions shown exemplarily in FIG. 23B, the optical power can decrease. Each curve in each subregion can have its own convex curve or function, as also exemplarily shown in FIG. 23B.

[0098] In the first to third embodiments, the diameter of the near region in a plan view may be 1.2 to 2.5 mm. At least within this range, it has been demonstrated that the depth of focus for near vision and / or intermediate vision can be increased and / or the image quality for far vision can be improved, as will be shown in the specific examples below.

[0099] <Embodiments 1' to 3'> Embodiment 1' is a three-zone EDOF. Figures 26 to 28 correspond to Embodiment 1'. Embodiment 1', Embodiment 2' (three-zone EM-IOL, not shown), and Embodiment 3' (three-zone multifocal lens, not shown) each include a distance region concentric with and including the lens center O, a near region located radially outward from the distance region O, and an outer region located radially outward from the near region and correcting vision for distance vision. Similarly to the distance regions of Embodiments 1 to 3, the outer region has a reduced power to provide negative longitudinal spherical aberration that at least partially offsets the positive longitudinal spherical aberration caused by the cornea.

[0100] In embodiments 1' to 3', at least one of the boundaries between different sub-regions within the near region, the boundary between any of sub-regions 1 to 3 and the far region when the near region and the far region are adjacent, and the boundary between any of sub-regions 1 to 3 and the far region when the near region and the outer region are adjacent, the change in power may be continuous or discontinuous, or the power may jump.

[0101] The inner diameter of the near region in plan view may be 1.4 to 2.2 mm, and the outer diameter may be 2.6 to 3.5 mm. As shown in the specific examples below, it has been demonstrated that at least within this range, the depth of focus for near vision and / or intermediate vision can be increased and / or the image quality for far vision can be improved. In these embodiments, too, the optical power can decrease in the first subregion, i.e., the positive add power deviation region, and furthermore, in the first subregion, the dependence of the optical power on the radial distance, i.e., the corresponding curve or function, can be concave, as exemplarily shown in Figure 26B. In the third subregion, i.e., the negative add power deviation region, the optical power can decrease. Furthermore, in the third subregion, the dependence of the optical power on the radial distance, i.e., the corresponding curve or function, can be convex. The third subregion can also be further divided into subregions, such as the two subregions of the third subregion shown exemplarily in FIG. 26B. In each of these subregions, the optical power can decrease. Each curve in each subregion can have its own convex curve or function, as also exemplarily shown in FIG. 26B.

[0102] <Embodiment 4> The fourth embodiment shows variations of the sub-regions. Figures 29 to 40 correspond to the fourth embodiment. In this embodiment, too, the optical power can decrease in the first subregion, i.e., the positive add power deviation region. Furthermore, in the first subregion, the dependence of the optical power on the radial distance, i.e., the corresponding curve or function, can be concave, as shown by way of example in Figures 29A, 29B, 29C, 29D, 31A, 31B, 31C, 31D, 33A, 33B, 35A, 35B, 35C, 37B, 37C, 37D, and 37E. The curve or function in the first subregion can also increase, as shown by way of example in Figures 37D and 37E. In the third subregion, i.e., the negative add power deviation region, the optical power can decrease. Furthermore, in the third subregion, the dependence of the optical power on the radial distance, i.e., the corresponding curve or function, can be convex, as shown by way of example in Figures 29A, 29B, 29D, 31A, 31B, 31C, 31D, 33A, 33C, 35A, 35B, 37B, 37C, 37D, and 37E. The curve or function in the third subregion can also be concave, as shown by way of example in Figures 33B and 33D. The curve or function in the third subregion can also increase, as shown by way of example in Figures 37D and 37E. The third subregion can be further divided into sub-subregions, such as the two sub-subregions of the third subregion shown in Figures 29C and 29D (pattern c3d1). In each of these sub-subregions, the optical power can decrease, as shown in Figures 29C and 29D (pattern c3d1). Each curve in each sub-subregion can have its own convex curve or function, as shown in Figures 29C and 29D (pattern c3d1). Each of these sub-subregions can also have its own convex curve or function, as shown in Figures 29C and 29D (pattern c3d1).

[0103] The intraocular lens according to [Aspect Group 1] may be a toric lens.

[0104] [Aspect Group 2] [Mode Group 2] mainly exemplifies phakic intraocular lenses or implantable (or non-implantable) contact lenses. However, [Mode Group 2] can also be applied to general intraocular lenses. With phakic intraocular lenses or contact lenses, visual acuity is less affected by corneal spherical aberration. Therefore, it is not necessary to adopt an aspheric reference power profile W. As shown in Figure 41A of a two-zone EDOF design for a phakic intraocular lens or contact lens, before applying the present invention ("Flat"), the power of the near zone may be constant and the power of the far zone may be constant. Then, the present invention may be applied as shown in Figure 41B.

[0105] Of course, in [Mode Group 2], as described in [Mode Group 1], it is also possible to adopt "an aspherical reference power within a predetermined radial range in a virtual aspherical lens that has a predetermined base power at the lens center O and completely offsets the positive vertical spherical aberration caused by the cornea."

[0106] In this specification (particularly the fourth aspect of the present invention in [Means for solving the problems of the present invention]), the expression "reference power having a predetermined base power at the lens center O" is used to combine both (the top two paragraphs).

[0107] 42A and 42B relate to EDOFs with a three-zone design in phakic intraocular lenses or contact lenses. Fig. 43 shows many further variations in which the modifications of embodiment 4 are extended to [mode group 2]. In this group of embodiments, the optical power can also decrease in the first subregion, i.e., the positive add power deviation region. Furthermore, in the first subregion, the dependence of the optical power on the radial distance, i.e., the corresponding curve or function, can be concave, as shown by way of example in Figures 41B, 42B, and 43. The curve or function in the first subregion can also be increasing. In the third subregion, i.e., the negative add power deviation region, the optical power can be decreasing. Furthermore, in the third subregion, the dependence of the optical power on the radial distance, i.e., the corresponding curve or function, can be convex, as exemplarily shown in Figures 41B, 42B, and 43. The curve or function of the third subregion can also be concave. The curve or function of the third subregion can also be increasing. The third sub-region (NAPD) can be further divided into sub-sub-regions, as exemplarily shown in Figure 43. In each of these sub-sub-regions, the optical power can decrease, as exemplarily shown in Figure 43. Each of these sub-sub-regions can have its own convex or concave curve or function, as shown in some examples in Figure 43. The first sub-region (NAPD) may also comprise sub-sub-regions with concave and / or convex curves, for example, as also exemplarily shown in FIG.

[0108] the ophthalmic lens is a phakic intraocular lens or a contact lens; When the near area includes the lens center O, When the far region is disposed radially outward from the lens center O, the far region is disposed radially outward from the near region. The diameter of the near region in plan view may be 1.4 to 3 mm.

[0109] the ophthalmic lens is a phakic intraocular lens or a contact lens; When the far region includes the lens center O, the near area is disposed outside the far area when the radial direction is taken outward from the lens center O, an outer region disposed outside the near region and correcting vision for distance vision; The near region may have an inner diameter of 1.6 to 2.4 mm and an outer diameter of 2.9 to 3.6 mm in plan view.

[0110] The ophthalmic lens may be a toric lens.

[0111] Each example (preferred example, modified example) described in the mode group 1 may be applied to the mode group 2.

[0112] Furthermore, although an intraocular lens (or an ophthalmic lens) has been exemplified in each group of aspects, the technical idea (concept) of the present invention can also be applied to an optical design method for designing an intraocular lens (or an ophthalmic lens).The technical idea (concept) of the present invention can also be applied to a manufacturing method for an intraocular lens (or an ophthalmic lens) in which an intraocular lens (or an ophthalmic lens) designed by the design method for an intraocular lens (or an ophthalmic lens) is manufactured by at least one of lathing, molding, and 3D printing.

[0113] The details of the present invention, including the mechanism thereof, will be described below. Hereinafter, the term "IOL of the present invention" will be used, but the contents of the following description are not intended to limit the present invention, and the term "IOL of the present invention" is used in the broad sense of an IOL that reflects the concept of the present invention (naturally including the above group aspects).

[0114] Further details of the invention A bifocal type EVR IOL improvement is described herein, and a two-zone optical design is provided as an example to illustrate the optical design of the present invention or the power profile of the present invention.

[0115] The present invention is applicable to the optical design of EM-IOLs, EDOFs, and multifocal lenses because the optical principle of these three IOL types is the same. This optical principle means that these IOLs have a base power for correcting distance vision and near and / or intermediate powers for correcting near and / or intermediate vision. As mentioned in [Aspect Group 1], the EDOF IOL is used as the primary example in this specification.

[0116] FIG. 1A shows a prior art (referred to herein as "Flat") aspheric EDOF IOL with a base power of 20.0D and an add power of 2.25D. Hereinafter, unless otherwise noted, power distribution graphs are shown with the horizontal axis representing radius and the vertical axis representing power. This IOL has two zones. The first zone is the inner zone (or central zone) and the second zone is the outer zone. The second zone has a base power for correcting distance vision. The inner first zone has a power that is 2.25D greater than the base power for correcting intermediate vision.

[0117] The power profile shown in Figure 1A is converted into an add graph (radius on the horizontal axis vs. add on the vertical axis) as shown in Figure 1B. The optical design of the EVR IOL shown in Figure 1 is commonly known as a two-zone optical design. The two-zone IOL shown in Figure 1 has pure bifocal properties.

[0118] The power profile shown by the dashed line graph in Figure 1 is for the base power of this IOL. This base power profile begins at a power value of 20.0D at a radius of 0 mm (radius from the lens center O) and decreases to approximately 16.4D at a radius of 3 mm. This base power profile can be designed to fully compensate for or partially reduce the spherical aberration of the average cornea of ​​a cataract patient. The spherical aberration of the average cornea is approximately 0.27 μm. The example base power profile shown in Figure 1 is designed to correct the 0.27 μm spherical aberration of the average cornea of ​​a cataract patient. In other words, this base power profile is the aspheric reference power profile W described above.

[0119] Correcting or reducing the spherical aberration of the cornea improves the image quality of the distance image reconstructed at the retina. In this specification, the base power profile is referred to as the Reference Base Power Profile (RBPP, previously mentioned in this specification).

[0120] This IOL has a power value of 22.25D at a radius of 0 mm (the radius at the center of the lens) and decreases with increasing radius up to a radius of 0.9 mm. The power profile from a radius of 0 mm to 0.9 mm is the power profile for the near region of this IOL.

[0121] This power profile for the near region is referred to herein as the reference near power profile. This reference near power profile is synonymous with the reference add power profile (RAPP) described below. The reference near power profile is a power profile (power graph shape) that is relatively similar to the RBPP. However, the power value at a specific radius is approximately 2.25 D (the design add power value of the IOL shown in Figure 1) greater than the power value of the RBPP at that specific radius.

[0122] The ADD power in Figure 1B is the design power profile of the EVR IOL minus the RBPP. In other words, the ADD power profile is the difference between the design power profiles of the EVR IOL and the RBPP.

[0123] Figure 2 shows the total power profile of the simulated eye model consisting of the cornea and EDOF IOL shown in Figure 1. The parameters of the simulated eye model are listed in Table 1. [Table 1] Anterior surface of cornea refers to the front surface of the cornea. Posterior surface of cornea refers to the posterior surface of the cornea. Aperture refers to the opening (it corresponds to the pupil diameter of the eye, but it is not an opening where no substance exists; this table lists the refractive index corresponding to the substance present in the opening). Anterior surface of intraocular lens refers to the front surface of the IOL. Posterior surface of lens refers to the posterior surface of the IOL. Note 1) Aspheric or aspheric curvature. The radius of curvature values ​​at the lens center for the various IOLs described herein are approximately 17.2 mm. Note 2) The facet spacing of the various IOLs described herein is approximately 0.7 mm. Note 3) The facet spacing of the various IOLs described herein is approximately 18.8 mm.

[0124] As shown in Figure 2, the total power profile has a pure bifocal characteristic. The corneal total power and EDOF base power are approximately 59.0D, and the corneal total power and EDOF add power are approximately 60.7D. The difference between the corneal total power and EDOF add power (60.7D) and the corneal total power and EDOF base power (59.0D) is 1.7D at the corneal surface. The value of 1.7D at the corneal surface corresponds to a viewing distance of 59cm. The value of 59cm (=0.59m) is 1.000 (this value is the refractive index of air) divided by the 1.7D difference power (D (diopter) units are (1 / m)).

[0125] Figure 3A shows how light rays from an intermediate distance are focused onto the retina by the cornea and the EDOF of Figure 1. Light rays from a distance of 59 cm in front of the cornea are also focused onto the retina by the cornea and the EDOF of Figure 1. Near objects located approximately 59 cm in front of the cornea can be clearly seen because light rays from nearby objects are focused onto the retina. However, objects in the near region that are not within the approximately 59 cm distance are not clearly seen and appear blurry.

[0126] The range of near distances at which objects in the near zone can be clearly perceived is affected by the power difference between the constant add profile and the reference base power for this IOL. The EDOF shown in Figure 1 narrows the depth of focus for intermediate vision. Figure 3B shows a wider depth of focus for intermediate vision. In Figure 3B, the range of intermediate distances at which objects can be clearly perceived is wider than the range in Figure 3A.

[0127] An ADD profile that is greater than the RBPP value by the ADD value of the IOL (e.g., greater than the ADD power of about 2.25 D) is referred to herein as a Reference ADD Profile (RAPP). The Reference ADD profile is shown by the dotted line in Figures 4, 5A, and 5C.

[0128] 4 is a diagram of the power profile of a two-zone EDOF with a base power of 20.0 D and an add power of 2.25 D (corresponding to embodiment 1). This IOL has an inner zone at the center of the lens for correcting intermediate vision and an outer zone surrounding the inner zone for correcting distance vision.

[0129] The inner region has four subregions. In sub-region a (corresponding to sub-region 1 in [Aspect Group 1]), there is a power profile segment whose power value is greater than RAPP. In subregion b (corresponding to subregion 2 in [Aspect Group 1]), there is a power profile segment whose power value is identical or similar to the RAPP power value ("identical or similar" with respect to power value may also be referred to as "equal"; the definition of "equal" has already been given). In subregion c (corresponding to subregion 3 in [Aspect Group 1]), there is a power profile segment whose power value is lower than the power value of the RAPP. In subregion d (corresponding to subregion 3 in [Aspect Group 1] (but a different subregion 3 from the above subregion 3)), there is also a power profile segment whose power value is lower than the RAPP power value and different from subregion c. The power value of the outer zone power profile is the same as or similar to the power value of the RBPP. The outer zone power profile can be designed to fully compensate or partially reduce the spherical aberration of the average cornea in a cataract patient's eye.

[0130] The power profile shown in Figure 4 can be represented by five polynomials. Each of the four subregions in the inner region and RAPP can be represented by a single polynomial.

[0131] In the following description, as illustrated in Figure 5A, a subregion with a power value greater than the RAPP value is referred to as a subregion with a positive add power deviation (PAPD), a subregion with a power value the same as or similar to the RAPP value is referred to as a subregion with a zero add power deviation (ZAPD), and a subregion with a power value less than the RAPP value is referred to as a subregion with a negative add power deviation (NAPD). NAPD is a negative value, and PAPD is a positive value. PAPD is also referred to herein simply as "positive power deviation." ZAPD is also referred to as "near zero power deviation" in this specification (the reason for adding "near" has already been explained). NAPD is also referred to herein simply as "negative power deviation."

[0132] 5 shows an example of the power profile of a two-zone EDOF with a base power of 20.0D and an add power of 2.25D (another example corresponding to embodiment 1). The add power graph (also called a "normalized add power graph") is a graph with radius (mm) on the horizontal axis and add power (D) on the vertical axis.

[0133] The power profiles shown in Figures 5A and 5C are converted into add graphs shown in Figures 5B and 5D, respectively. Unlike the IOL in Figure 4, the two IOLs shown in Figure 5 do not have a fourth subregion d.

[0134] The power profile of the radius vs. power (refractive power) graphs shown in Figures 5A and 5C can be expressed by four polynomials. The inner region in Figures 5A and 5C and each subregion of the three subregions in RAPP can be represented by a single polynomial. The radius versus add graph shown in FIG. 5B can be represented by two polynomials (for subregions a' and c') and two linear line equations (for subregion b' and the outer region). The normalized ADD profile of FIG. 5D can be represented by four linear equations.

[0135] 6A and 6B show the total power profiles of the simulated eye model consisting of the cornea and EDOF shown in FIGS. 5A and 5C, respectively. The total power profiles shown in FIGS. 6A and 6B differ from the total power profile shown in FIG. 2.

[0136] In the radius range of 0 mm to 0.9 mm, the total power profile of Figure 6 has various total power values ​​set, while the total power profile of Figure 2 has only one total power value (60.7D) set for viewing objects at intermediate distances.

[0137] Various total power values ​​of the IOL, greater or less than the 60.7D total power value shown in FIG. 6, provide a greater depth of focus for intermediate vision than the IOL of FIG. 1, as shown in FIG. 3B.

[0138] Sub-region a of the inner region of FIGS. 5A and 5B, which includes PAPD, has the function of extending the intermediate distance range of intermediate vision.

[0139] By providing one or more subregions of the inner region with NAPD, the power from the RAPP can be reduced, improving image quality for distance vision. The subregions of the inner region that function to reduce the RAPP power are subregions c and d in Figure 4 and subregion c in Figure 5. Reducing the RAPP power in these subregions is also expected to reduce the likelihood of halo and glare symptoms and the degree of visual impairment at night in dark environments.

[0140] The radial arrangement order of the subregions in the inner region of a two-zone IOL can be changed (as described above in [Aspect Group 1]). The subregions of the two-zone IOL in FIG. 4 are arranged in the following order from the lens center O toward the lens periphery (radial direction): first, the subregion with PAPD, second, the subregion with ZAPD, and third, the subregion with NAPD. Of course, other arrangements are also possible. For example, from the lens center, the subregion with ZAPD may be arranged first, then the subregion with PAPD, and third, the subregion with NAPD.

[0141] The size of each subregion of the inner region affects the optical properties and performance of the EDOF for correcting distance and intermediate vision. For example, if subregion b with ZAPD is too large compared to subregion a with PAPD and subregion c with NAPD, the optical performance of the EDOF for correcting distance and intermediate vision will be similar to an EDOF with a power profile such as that shown in Figure 1. If the region size of subregion c with NAPD is too large compared to subregion a with PAPD and subregion b with ZAPD, the optical performance of the EDOF for correcting intermediate vision will decrease, but the optical performance for correcting distance vision will improve.

[0142] The area ratio of each sub-region in the inner region can be determined by setting the radius value of these sub-regions. For example, the inner region has three sub-regions a (PAPD), b (ZAPD), and c (NAPD), and the radius of the inner region is 1 mm (diameter 2 mm). The area of ​​the inner region in this example is 3.142 mm 2 is. Assume that the area percentages of subregion a, subregion b, and subregion c relative to the entire inner region (near region) are 30%, 40%, and 30%, respectively. To achieve this, the radius value (ra) of subregion a is set to 0.548 mm, the radius value (rb) of subregion b is set to 0.837 mm, and the radius value (rc) of subregion c is set to 1 mm.

[0143] The reference base power profile (dashed line, RBPP) of the IOL shown in Figures 4 and 5 (both corresponding to embodiment 1) is designed to fully compensate for the spherical aberration (approximately 0.27 μm) of the average cornea of ​​a cataract patient. Meanwhile, the reference base power profile of the EVR IOL (or bifocal two-zone and three-zone IOLs) according to the present invention is not limited to compensating for the 0.27 μm spherical aberration of the cornea. The reference base power profile of the EVR IOL according to the present invention can be designed to compensate for different corneal spherical aberration values, for example, 0.20 μm, 0.16 μm, 0.10 μm, and 0 μm. It can also be designed to fully correct or partially reduce a specific longitudinal spherical aberration (longitudinal spherical aberration of a geometric optical system) of a human cornea model that is modeled or defined based on a database or statistical data of the human cornea.

[0144] The power profile according to the present invention, as exemplified herein, can be set by calculating or designing the anterior and posterior surface shapes of the optic portion of the IOL. By utilizing specific known design or manufacturing techniques, it is possible to set an intended power profile for the anterior and posterior surface shapes of the optic portion of the IOL. Specific known design techniques include various common methods or approaches, such as calculations using geometric optics and numerical methods, calculations using ray tracing, and design using commercially available optical design software.

[0145] The aspheric sag or shape that produces the power profile can be on the anterior or posterior lens surface, or on both surfaces. The EVR IOL of the present invention can be designed and manufactured to correct astigmatism in phakic patients' eyes. This is accomplished by providing a toric or cylindrical surface on the anterior or posterior lens optic. In a toric-type EVR IOL, the aspheric sag or shape that produces the power profile of the EVR IOL of the present invention is provided on a lens optic surface that is not a toric surface. For information on sag values, see WO2018 / 043366.

[0146] 7 shows yet another example of the first embodiment of the present invention. The radius of the inner region is 0.9 mm. There are four sub-regions in the inner region. Sub-area a is equipped with a PAPD, the radius of which is 0.5 mm. Subregion b is provided with a ZAPD and exists between radii ra and rb (0.7 mm). Subregion c is provided with NAPD and lies between radii rb and rc (0.8 mm). Subregion d is provided with NAPD and lies between radii rc and rd (0.9 mm). If the total area of ​​the inner region is taken as 100%, the percentages of the areas of subregions a, b, and c plus subregion d (c + d) are approximately 31%, 30%, and 39%, respectively. The RAPP is approximately 2.25D larger than the reference base power (RBPP).

[0147] To compare the optical characteristics and performance of this IOL (Embodiment 1, Figure 7) with the conventional ("Flat") EDOF shown in Figure 1, optical evaluation and retinal image simulation were performed using the model eye parameters shown in Table 1 and the optical design software Zemax®13. Zemax is a registered trademark of Radiant Zemax LLC. The optical characteristics evaluated were the TFR (Through Focus Response) and the MTF (Modulated Transfer Function).

[0148] Fig. 8 shows the TFR as a function of pupil diameter at a spatial frequency of 50 lp / mm (line pairs / mm) for the simulated eye model using the EDOF shown in Fig. 1 (prior art) and Fig. 7 (embodiment 1). Fig. 9 shows the TFR as a function of pupil diameter at a spatial frequency of 100 lp / mm.

[0149] The TFR indicates the defocus and MTF characteristics of the simulated EDOF. The MTF represents the image quality reconstructed by the optical system of the simulated eye model. As shown in FIG. 8, a pupil diameter of 3 mm provides high MTF values ​​at approximately 0 D (far distance) and approximately 1.7 D of defocus (at a distance of approximately 59 cm) in both the conventional technology and the embodiment. A pupil diameter of 3 mm is a value commonly used or assumed as the average pupil diameter of an aphakic patient's eye under normal lighting conditions.

[0150] The depth of focus of an EVR IOL is the range of defocus (or range of viewing distances) over which objects are still clearly or adequately visible to the aphakic patient's eye. Herein, an MTF value of 0.1 or greater at a spatial frequency of 50 lp / mm is considered useful for correcting visual acuity, and an MTF value of 0.05 or greater at a spatial frequency of 100 lp / mm is considered useful for correcting visual acuity. A state above these values ​​is also referred to as "adequate." Herein, "depth of focus" refers to the range of object distances (defocus values ​​on the horizontal axis of the graph) that have adequate MTF values. A wide range is also referred to as a "wide (or large) depth of focus." The depth of focus at a spatial frequency of 50 lp / mm is shown in the TFR graph for a pupil diameter of 2 mm in Figure 8. The depth of focus at a spatial frequency of 100 lp / mm is shown in the TFR graph for a pupil diameter of 2 mm in Figure 9.

[0151] As shown in the TFR graphs for pupil diameters of 2 mm and 2.5 mm in FIG. 8 and the TFR graphs for pupil diameters of 2 mm, 2.5 mm, and 3 mm in FIG. 9, the depth of focus for intermediate vision in the present invention is set wider in the horizontal axis direction than the depth of focus of IOLs of the prior art.

[0152] It is known that under normal lighting conditions, images appear sharper (better) with a smaller pupil diameter than with a larger pupil diameter. In a two-zone IOL with an inner zone in a lens optical system for correcting intermediate and / or near vision, the MTF (i.e., a parameter that determines whether an image appears sharper or sharper) for near and intermediate vision is higher with smaller pupil diameters (e.g., 2mm and 2.5mm) than with larger pupil diameters (e.g., 3.5mm and 4mm). This is illustrated in Figures 8 and 9, where the MTF values ​​are higher for pupil diameters of 2mm and 2.5mm, ranging from 0.75D (visual distance of approximately 133cm) to 2.25D (visual distance of approximately 44cm), than for pupil diameters of 3.5mm and 4mm (0.75-2.25D). Hereinafter, intermediate vision and / or near vision will also be referred to simply as "intermediate-near vision," and intermediate vision and / or near vision will also be referred to simply as "intermediate-near vision."

[0153] The above also means that the depth of focus and quality of vision for near and intermediate vision with a small pupil diameter (e.g., less than 2.75 mm) are superior to the depth of focus and quality of vision for near and intermediate vision with a large pupil diameter (e.g., greater than 3.25 mm). As a result, aphakic patients are thought to view objects at close range with a small pupil diameter (e.g., with a pupil diameter smaller than the average pupil diameter of 3 mm). In other words, a smaller pupil diameter is better for visual acuity. This is also true for aphakic patients. Even aphakic patients can adjust the size of their pupil diameter to achieve higher visual acuity. A smaller pupil diameter improves visual acuity rather than a larger one. Therefore, aphakic patients use a smaller pupil diameter.

[0154] The MTF for distance vision of the IOLs of the present invention is also higher than that of the prior art IOLs, as evidenced by the higher MTF value (vertical axis value) of the IOLs of the present invention at a defocus value of approximately 0 D (horizontal axis value) than that of the prior art IOLs in the TFR graphs for pupil diameters of 2.5 to 4 mm shown in Figures 8 and 9.

[0155] When the pupil diameter is large, a two-zone optical design IOL makes distant objects appear sharper than when the pupil diameter is small. As the pupil diameter increases, the area of ​​the outer region of the lens optics (to correct distance vision) that focuses light rays onto the retina also increases. This increases the amount of light rays that are focused onto the retina. As a result, objects appear clearer than when the pupil diameter is small.

[0156] The MTF (representing image quality) for distance vision when the pupil diameter is large (e.g., 4 mm) is higher (better) than when the pupil diameter is small (e.g., 2 mm). This is demonstrated by the fact that the vertical axis values ​​around 0D (far distance) are higher in the TFR graphs for pupil diameters of 3.5 mm and 4 mm in Figures 8 and 9 than in the TFR graphs for pupil diameters of 2 mm and 2.5 mm.

[0157] The primary function of the EDOF is to correct distance vision. The benefit of the present IOL for improving distance image quality or image appearance is demonstrated by the image simulation results shown in Figures 10-12. The distance image obtained with the present IOL is less blurry than the distance image obtained with the prior art IOL, making the distance image sharper.

[0158] The distance vision MTF ("Segment" in Figures 13 and 14) of the EDOF according to the present invention is higher than the MTF of the prior art EDOF at pupil diameters of 3 mm and 4 mm. This is shown in the MTF graphs of Figures 13 and 14, respectively. These MTF graphs were simulated at distances of 6 m, 12 m, and 25 m.

[0159] Figures 13 and 14 show simulated MTF graphs for both IOLs at distances of 6 m, 12 m, and 25 m with pupil diameters of 3 mm and 4 mm. These graphs demonstrate that the distance visual acuity MTF of the EDOF of the present invention is higher than that of the prior art EDOF. In these graphs, a spatial frequency of 50 lp / mm corresponds to a visual acuity of 0.5 (Snellen equivalent 20 / 40) or a logMAR (logMAR) of 0.3, while a spatial frequency of 100 lp / mm corresponds to a visual acuity of 1 (Snellen equivalent 20 / 20) or a logMAR of 0.

[0160] The benefit of the present IOL in extending depth of focus for intermediate vision is shown in Figures 15-19. As can be seen in the TFR graph for a pupil diameter of 3 mm in Figure 8, the best viewing distance for the prior art IOL and the present IOL is approximately 59 cm (corresponding to a defocus of 1.7 D).

[0161] The images at different distances (40-60 cm) in Figures 15, 16, and 17 are simulated images with pupil diameters of 2, 3, and 4, respectively. Distances from 40 cm to 55 cm are closer to the cornea of ​​the simulated eye model than the optimal viewing distance of 59 cm. The images at different distances (70-110 cm) in Figures 18 and 19 are simulated images with pupil diameters of 2 mm and 3 mm. These distances are farther than the optimal viewing distance (59 cm) for both intraocular lenses.

[0162] In Figure 15 (pupil diameter 2 mm), the Landolt C (Landolt ring) patterns are clearly visible in images at distances of 60 cm and 55 cm for the prior art intraocular lens and the IOL of the present invention. In images at distances of 50 to 40 cm, which is closer to the cornea than the best viewing distance, the ring pattern of the IOL of the present invention is clearer than the ring pattern of the prior art IOL.

[0163] In Figures 16 (pupil diameter 3 mm) and 17 (pupil diameter 4 mm), the ring patterns are clearly visible for both IOLs at distances of 60 cm and 55 cm. For images at distances of 50 to 40 cm, the ring pattern for the IOL of the present invention is more distinct than that of the prior art IOL.

[0164] In Figure 18 (pupil diameter 2 mm) and Figure 19 (pupil diameter 3 mm), the ring pattern in the image at a distance of 90 cm to 110 cm for the IOL of the present invention is clearer than the ring pattern for the IOL of the prior art.

[0165] The image simulation results shown in Figures 15 to 19 indicate that the depth of focus for intermediate vision of the EDOF, which is one of the IOLs of the present invention, is wider than the depth of focus for intermediate vision of the EDOF of the prior art. In this specification, "wide depth of focus" means that the distance range (the range of the horizontal axis in the graph) over which an appropriate MTF value can be obtained is wide.

[0166] The advantage of the EDOF of embodiment 1 over the prior art EDOF is that when the pupil diameter is less than 3 mm, the depth of focus is wider for near and intermediate vision, and the MTF value for far vision is higher for all pupil diameters.

[0167] Figure 20A shows the power profile of a prior art aspheric EM-IOL (hereinafter simply referred to as EM-IOL) with a base power of 20.0D and an add power of 1.0D. This IOL uses a two-zone type extended monofocal optical design. The IOL has two optical zones that actually reflect this design. The outer zone has a RBPP for correcting distance vision. The inner zone has a power 1.0D greater than the base power to correct intermediate vision.

[0168] Figure 20B shows an EM-IOL according to the present invention (corresponding to embodiment 2). The radius of the inner region is 0.9 mm. There are four sub-regions in the inner region. Sub-area a is equipped with a PAPD, the radius of which is 0.5 mm. Subregion b is provided with a ZAPD and exists between radii ra and rb (0.7 mm). Subregion c is provided with NAPD and lies between radii rb and rc (0.8 mm). Subregion d is provided with NAPD and lies between radii rc and rd (0.9 mm). If the total area of ​​the inner region is taken as 100%, the area of ​​subregions a, b, and c plus subregion d (c + d) is approximately 31%, 30%, and 39%, respectively. The RAPP is approximately 1.0 D greater than the reference base power (RBPP).

[0169] Figure 21 shows the TFR as a function of pupil diameter at a spatial frequency of 50 lp / mm (line pairs / mm) for the simulated eye model using the EM-IOL shown in Figure 20A (prior art) and Figure 20B (embodiment 2). Figure 22 shows the TFR as a function of pupil diameter at a spatial frequency of 100 lp / mm.

[0170] The depth of focus of the EM-IOL of the present invention (embodiment 2) at pupil diameters of 2.5 mm and 3 mm and at a spatial frequency of 50 lp / mm is wider than that of the EM-IOL of the prior art, as shown in Figures 21A, 21B, 22A, and 22B, respectively. The MTF values ​​near 0D (distance of far vision) for the EM-IOL of the present invention (embodiment 2) are higher than those of the EM-IOL of the prior art at all pupil diameters.

[0171] The advantages of the EM-IOL of embodiment 2 over the prior art EM-IOL are that when the pupil diameter is less than 3 mm, the depth of focus for intermediate vision is wider and the MTF value for distance vision is higher at all pupil diameters.

[0172] Figure 23A shows the power profile of a prior art multifocal lens (corresponding to embodiment 3) with a base power of 20.0D and an add power of 3.25D. This IOL uses a two-zone multifocal optical design. The IOL has two optical zones that actually reflect this design. The outer zone has a RBPP for correcting distance vision. The inner zone has a power that is 3.25D greater than the base power to correct intermediate vision.

[0173] Figure 23B shows a multifocal lens according to the present invention. The radius of the inner region is 1 mm. There are four sub-regions in the inner region. Sub-area a is equipped with a PAPD, the radius of which is 0.45 mm. Subregion b is provided with a ZAPD and exists between radii ra and rb (0.71 mm). Subregion c is provided with NAPD and lies between radii rb and rc (0.875 mm). Subregion d is provided with NAPD and lies between radii rc and rd (1 mm). If the total area of ​​the inner region is 100%, the areas of subregions a, b, and c plus subregion d (c + d) are approximately 20%, 30%, and 50%, respectively. The RAPP is approximately 3.25D larger than the reference base power (RBPP).

[0174] Figure 24 shows the TFR as a function of pupil diameter at a spatial frequency of 50 lp / mm (line pairs / mm) for the simulated eye model using the multifocal lenses shown in Figure 23A (prior art) and Figure 23B (embodiment 3). Figure 25 shows the TFR as a function of pupil diameter at a spatial frequency of 100 lp / mm.

[0175] The depth of focus for the multifocal lens of the present invention (embodiment 3) at pupil diameters of 2.5 mm and 3 mm and at a spatial frequency of 50 lp / mm is wider than that of the multifocal lens of the prior art, as shown in Figures 24A, 24B, 25A, and 25B, respectively. The MTF values ​​near 0D (distance of far vision) for all pupil diameters are higher for the multifocal lens of the present invention (embodiment 3) than for the multifocal lens of the prior art.

[0176] The advantage of the multifocal lens of embodiment 3 over prior art multifocal lenses is that when the pupil diameter is less than 3 mm, the depth of focus is wider for near and intermediate vision, and the MTF value for far vision is higher at all pupil diameters.

[0177] Figure 26A shows the power profile of a prior art three-zone EDOF, and Figure 26B shows the power profile of a three-zone EDOF according to the present invention (embodiment 1').

[0178] The three-zone EDOF of embodiment 1' has three zones. The first zone, which includes the lens center O, is used to correct distance vision, and the second zone is used to correct intermediate vision. The second zone is an annular zone surrounding the first zone and has a power greater than the base power. The third zone is used to correct distance vision. The third zone is an annular zone surrounding the second zone.

[0179] The second region exists between the radius ra0 (0.6 mm) and the radius rd (1.2 mm). This second region has four subregions (a, b, c, and d). The RAPP of the second region is 2.25D larger than the RBPP.

[0180] In this example, subregion a has a positive ADD deviation, subregion b has zero ADD deviation, and subregions c and d have negative ADD deviation.

[0181] The sub-area a exists between the radius ra0 (0.6 mm) and the radius ra (0.885 mm). Subregion b exists between radius ra (0.885 mm) and radius rb (1.05 mm). The subregion c exists between the radius rb (1.05 mm) and the radius rc (1.125 mm). The subregion d exists between the radius rc (1.125 mm) and the radius rd (1.2 mm). If the total area of ​​the inner region is 100%, the area of ​​subregion a, subregion b, and subregion c plus subregion d (c + d) is approximately 39%, 30%, and 31%, respectively.

[0182] FIG. 27 shows TFRs depending on pupil diameter at a spatial frequency of 50 lp / mm (line pair / mm) of the simulated eye model using the EDOF shown in FIG. 26A (prior art) and FIG. 26B (embodiment 1′).

[0183] 28 shows the MTF as a function of pupil diameter near 0D (distance for far vision) for the conventional technology and embodiment 1'. The MTF graph for embodiment 1' is higher than the MTF value for the conventional technology, except that the conventional technology showed a higher MTF value at a pupil diameter of 2 mm.

[0184] The above results demonstrate that the three-zone EDOF embodiment 1' offers the advantage of extending the depth of focus for intermediate vision at smaller (average) pupil diameters while improving image quality for distance vision at all pupil diameters compared to prior art three-zone EDOFs.

[0185] FIG. 29 shows the power profiles of three IOLs (pattern c1, pattern c2, and pattern c3d1) with different NAPD graphs for subregions in the medial region. The absolute value of NAPD in subregion c1 of the IOL with pattern c1 is greater than the absolute value of NAPD in subregion c2 of the IOL with pattern c2. The NAPD value is, in other words, the amount of reduction from RAPP, or, in yet another way, the average value of the negative values ​​obtained by subtracting the RAPP value from the vertical axis value of each pattern c graph at each horizontal axis value within subregion c(+d). The "absolute value of NAPD" is the absolute value of the average value, and is, for example, the average width along the vertical axis when the horizontally hatched portion of Figure 5A is viewed along the horizontal axis. The sum of the absolute value of the NAPD of subregion c3 and the absolute value of the NAPD of subregion d1 in the IOL with pattern c3d1 is greater than the absolute value of the NAPD of subregion c2 in the IOL with pattern c2.

[0186] The TFRs of IOLs at pupil diameters of 2.5 mm, 3 mm, and 3.5 mm are shown in Figure 30. It has been demonstrated that IOLs with larger absolute NAPDs provide better distance MTF values ​​(at defocus near 0 D) than IOLs with smaller absolute NAPDs. This means that the image quality of distance vision in aphakic patients wearing an IOL with a larger absolute NAPD is better than that of aphakic patients wearing an IOL with a smaller absolute NAPD. This effect occurs because an IOL with a larger absolute NAPD can focus a larger amount of light rays coming from farther away onto the retina than an IOL with a smaller absolute NAPD.

[0187] The depth of focus for near and intermediate vision with these three IOLs at pupil diameters of 2.5 mm and 3 mm is relatively similar. IOLs with smaller absolute NAPD values ​​provide better MTF values ​​for near and intermediate vision across a defocus range of 0.75 D (approximately 133 cm) to 2.25 D (approximately 44 cm) than IOLs with larger absolute NAPD values. This effect occurs because IOLs with smaller absolute NAPD values ​​can focus a larger amount of light onto the retina from near and intermediate distances than IOLs with larger absolute NAPD values.

[0188] FIG. 31 shows the power profiles of three EDOFs (pattern b1, pattern b2, pattern b3) with different area ratios of subregions having ZAPDs. The inner diameter of each IOL in Figure 31 is 0.9 mm. If the circular area of ​​the inner region of the lens with a radius of 0.9 mm is taken as 100%, then the radius of the subregion that accounts for 40% of that area and has PAPD, the radius of the subregion that accounts for 20% of that area and has ZAPD, and the radius of the subregion that accounts for 40% of that area and has NAPD can be calculated. In the IOL of pattern b1, the area percentages of the subregions with PAPD, the subregions with ZAPD, and the subregions with NAPD are 40%, 20%, and 40%, respectively. In the IOL of pattern b2, the area ratio of each subregion is PAPD:ZAPD:NAPD=30%:40%:30%. In the IOL of pattern b3, the area ratio of each subregion is PAPD:ZAPD:NAPD=20%:60%:20%. The IOL with pattern b1 has the lowest proportion of the area of ​​the subregion with ZAPD, and the IOL with pattern b3 has the highest proportion of the area of ​​the subregion with ZAPD.

[0189] Figure 32 shows the TFRs for the IOLs shown in Figure 31 for pupil diameters of 2.5 mm, 3 mm, and 3.5 mm. It can be seen that IOLs with a higher area percentage of subregions with ZAPDs have higher MTF values ​​for near and intermediate vision over a defocus range from 1 D (approximately 100 cm) to approximately 2.2 D (approximately 45 cm) than IOLs with a lower area percentage of subregions with ZAPDs. The image quality for intermediate vision with IOLs with a higher area percentage of subregions with ZAPDs is higher than that of IOLs with a lower area percentage of subregions with ZAPDs. This is because IOLs with a higher area percentage of subregions with ZAPDs focus a much larger amount of light coming from intermediate distances onto the retina than IOLs with a lower area percentage of subregions with ZAPDs.

[0190] The distance MTF value of the b1 IOL at a pupil diameter of 2.5 mm is higher than that of the b2 and b3 IOLs. Conversely, its near and intermediate MTF value is lower than that of the b2 and b3 IOLs. The b1 IOL, which has a smaller proportion of the area of ​​the subregion with ZAPD and a larger proportion of the area of ​​the subregion with NAPD, focuses a much larger amount of light coming from farther away onto the retina than the b2 and b3 IOLs at a pupil diameter of 2.5 mm (the b1 IOL has a larger MTF value near 0D than the other patterns). Therefore, its distance MTF value is higher than that of the b2 and b3 IOLs. The distance MTF values ​​of these three IOLs are relatively similar at pupil diameters of 3 mm and 3.5 mm.

[0191] FIG. 33 shows the power profiles of four EDOFs (pattern a1c1, pattern a1c2, pattern a2c1, pattern a2c2) in which the power profiles of the subregions having the added power are different from each other. The PAPD of the IOLs with patterns a1c1 and a1c2 is greater than the PAPD of the IOLs with patterns a2c1 and a2c2. The PAPD value is, in other words, the increase from RAPP, or, in other words, the average value of the positive values ​​obtained by subtracting the RAPP values ​​from the vertical axis values ​​of the graphs for patterns a and c at each horizontal axis value within subregion a. For example, it is the average width along the vertical axis when the vertically hatched portion of Figure 5A is viewed horizontally. The absolute values ​​of the NAPD of the IOLs of patterns a1c1 and a2c1 are greater than the absolute values ​​of the NAPD of the IOLs of patterns a1c2 and a2c2.

[0192] The TFRs of the IOLs shown in Figure 33 for pupil diameters of 2.5 mm, 3 mm, and 3.5 mm are shown in Figure 34. It has been demonstrated that IOLs with larger absolute values ​​of NAPD (patterns a1c1 and a2c1) provide higher distance MTF values ​​at defocus near 0 D than IOLs with smaller absolute values ​​of NAPD (patterns a1c2 and a2c2).

[0193] The IOLs with PAPD-equipped subregions (patterns a1c1 and a1c2) and with a high area ratio of the subregions have appropriate MTF values ​​for intermediate and near vision in the defocus range from 2D (approximately 50 cm distance) to approximately 2.5D (approximately 40 cm distance), and the MTF values ​​for intermediate and near vision of the IOLs are higher than the MTF values ​​for intermediate and near vision of the IOLs with a small area ratio of PAPD-equipped subregions (patterns a2c1 and a2c2).

[0194] FIG. 35 shows the power profiles of an IOL with a power jump (hereinafter referred to as a power jump IOL) and an IOL without a power jump (hereinafter referred to as a no-power jump IOL). The PAPD of the power jump IOL is larger than the PAPD of the non-power jump IOL. The absolute value of the NAPD of the power jump IOL is greater than the absolute value of the NAPD of the non-power jump IOL.

[0195] Figure 36 shows the TFRs of the IOLs shown in Figure 35 for pupil diameters of 2.5 mm, 3 mm, and 3.5 mm. The power jump IOL with a large PAPD provides adequate MTF values ​​for intermediate and near vision in a defocus range of 1 D (approximately 100 cm) to approximately 2.0 D (approximately 50 cm), and the MTF values ​​are higher for intermediate and near vision than the non-power jump IOL with a small PAPD. However, for a defocus range of 2 D or more (50 cm or less), the power jump IOL with a large PAPD provides higher MTF values ​​for intermediate and near vision. The distance vision MTF value at defocus near 0D was higher for power jump IOLs with a large absolute value of NAPD than for non-power jump IOLs with a small absolute value of NAPD.

[0196] In the present invention, the power jump between the subregions in the inner region and the power jump between the inner and outer regions in the two zones can be utilized to change the power profile of the subregions with PAPD and NAPD. By changing the power profile of the subregions in the inner region, the PAPD and NAPD values ​​can be changed. As a result, the TFR characteristics of the IOL can be adjusted to provide the intended performance of distance vision correction and intermediate-near vision correction.

[0197] The order of the subdomains comprising PAPD, ZAPD, and NAPD in the present invention can be varied.

[0198] FIG. 37 shows examples of power profiles of four EDOFs (Flat (only this is a conventional technique), CenterFlat, MiddleFlat, and OuterFlat) in which the radial order of the subregions including PAPD, ZAPD, and NAPD is different.

[0199] In CenterFlat, from the subregion including the lens center O to the subregion outside the inner region, the order is a subregion with ZAPD, a subregion with PAPD, and a subregion with NAPD. In OuterFlat, the order is a subregion with NAPD, a subregion with PAPD, and a subregion with ZAPD.

[0200] The TFRs of these IOLs at pupil diameters of 2.5 mm, 3 mm, and 3.5 mm are shown in Figure 38. At all pupil diameters, the distance visual acuity MTF values ​​for CenterFlat at defocus near 0D are higher than those for Flat (conventional technology), MiddleFlat, and OuterFlat. At all pupil diameters, the distance visual acuity MTF values ​​for MiddleFlat and OuterFlat IOLs at defocus near 0D are higher than those for Flat IOL.

[0201] The depth of focus for CenterFlat at pupil diameters of 2.5mm and 3mm is wider than that of Flat. When defocus exceeds 2D, the MTF value of CenterFlat is higher than that of Flat at all pupil diameters. This means that the image quality of CenterFlat is better than that of Flat at distances less than 50cm.

[0202] The depth of focus for MiddleFlat at a pupil diameter of 2.5 mm is wider than that of Flat. When defocus exceeds 2.2D, the MTF value for MiddleFlat is higher than that of Flat at all pupil diameters. When defocus exceeds 1.7D, the MTF value for OuterFlat is higher than that of Flat at all near visual acuity.

[0203] Figure 39 shows the power profiles of two EDOFs (OuterHigher a1c1 and OuterHigher a2c2) that are arranged in a different radial order from the EDOFs shown in Figure 37. From the subregion including the lens center O to the subregion outside the inner region, the subregions are, in order, a subregion with NAPD, a subregion with ZAPD, and a subregion with PAPD. In the OuterHigher a2c2 region, there is a power jump between each subregion.

[0204] The TFRs of these intraocular lenses at different pupil diameters are shown in Figure 40. The distance visual MTF values ​​at defocus near 0D for OuterHigher a1c1 and OuterHigher a2c2 are higher than that of the conventional Flat lens. The depth of focus for near and intermediate visual acuity for these three IOLs is relatively the same regardless of pupil size.

[0205] The intermediate-near vision MTF value during defocus is less than approximately 1.6 D. The intermediate-near vision MTF values ​​for OuterHigher a1c1 and OuterHigher a2c2 are slightly higher than those for Flat.

[0206] These results indicate that different orders of the sub-regions comprising PAPD, ZAPD, and NAPD in the inner region of the present invention can provide several advantages over prior art IOLs, such as higher distance vision image quality (MTF value) for different pupil diameters, wider depth of focus at a specific pupil diameter, and higher MTF value at near distances. Also, different orders can provide different advantages over prior art IOLs.

[0207] The present invention is applicable to other prior art two-zone and three-zone type ophthalmic lenses ([Aspect Group 2]) with a constant base power profile and a constant add power profile, as illustrated in Figures 41A and 42A.

[0208] In these figures, the base power at different radius values ​​is 20.0D, and the add power at different radius values ​​is 2.25D.

[0209] Unlike the reference base power profiles of the prior art "Flat" two-zone IOL of Figure 1 and the prior art "Flat" three-zone IOL of Figure 26A, which are designed to compensate for or reduce the spherical aberration of the average human cornea, the base power profiles of Figures 41A and 42A have a constant (20.0 D) power value. These power profiles are not intended to correct or reduce the spherical aberration of the human cornea.

[0210] Advantages such as higher distance image quality, wider depth of focus for near and intermediate vision, and better near image quality for near distances, or improved visual acuity, can also be obtained by applying the present invention to the prior art IOLs shown in Figures 41A and 42A.

[0211] FIG. 41B shows an example of the power profile of the prior art two-zone IOL shown in FIG. 41A adapted to improve distance and near and intermediate vision with the present invention. FIG. 42B shows an example of the power profile of the prior art three-zone IOL shown in FIG. 42A adapted to improve distance and near and intermediate vision with the present invention.

[0212] For the EVR IOL of the present invention, the preferred radius of the inner region having a two-zone type and an add power is 0.6 to 1.25 mm (diameter 1.2 to 2.5 mm). For the phakic EVR IOL of the present invention, the preferred radius of the inner region is 0.7 to 1.5 mm (diameter 1.4 to 3 mm). For the EVR contact lens of the present invention, the preferred radius of the inner region is 0.85 to 1.75 mm (diameter 1.7 to 3.5 mm).

[0213] The three-zone type EVR IOL of the present invention has three zones. The first zone, which includes the center of the lens, is used to correct distance vision, and the second zone is used to correct near and / or intermediate vision. The second zone is an annular zone surrounding the first zone and has a power greater than the base power. The third zone is used to correct distance vision. The third zone is an annular zone surrounding the second zone.

[0214] The inner diameter of the second region at the boundary between the first region and the second region having the added power preferably has a value of 0.7 to 1.1 mm (diameter 1.4 to 2.2 mm). The outer diameter of the second region at the boundary between the second region and the third region preferably has a value of 1.3 to 1.75 mm (diameter 2.6 to 3.5 mm). In the case of a three-zone type phakic EVR IOL of the present invention, the inner diameter of the second zone preferably has a value of 0.8 to 1.2 mm (diameter 1.6 to 2.4 mm), and the outer diameter of the second zone preferably has a value of 1.45 to 1.9 mm (diameter 2.9 to 3.6 mm). In the case of a three-zone type contact lens of the present invention, the inner diameter of the second zone preferably has a value of 0.9 to 1.45 mm (diameter 1.8 to 2.9 mm), and the outer diameter of the second zone preferably has a value of 1.7 to 2.3 mm (diameter 3.4 to 4.6 mm).

[0215] The preferred add power for the EVR IOL of the present invention and the two-zone and three-zone types of phakic EVR IOL is 1 to 4D at the optical surface of the IOL, and for the EVR contact lens of the present invention, 0.75 to 4D at the corneal surface. In addition, in [Mode Group 1], the preferred add power of the 2-zone type and 3-zone type EM-IOL of the present invention is 1 to 2D, that of the EDOF of the present invention is 2 to 2.75D, and that of a multifocal lens is 2.75D or more.

[0216] The sub-regions with add power for correcting a small range of near vision, intermediate vision, and distance vision very close to intermediate vision are a sub-region with PAPD, a sub-region with ZAPD, and a sub-region with NAPD. In the present invention, the sub-regions with add power may not only include two or more sub-regions with NAPD, but also two or more sub-regions with ZAPD and two or more sub-regions with PAPD.

[0217] Subregions with PAPD may have PAPD graphs with different shapes. Figure 43 shows several examples of possible PAPD graphs in addition to the PAPD graphs shown in the previous figures of the EVR IOL of the present invention in this specification. Of course, other PAPD graph shapes not shown in this specification are also applicable to the EVR IOL of the present invention. In addition, the NAPD shapes shown in this specification may be modified as appropriate. In addition, PAPD graph shapes not shown in the figures of this specification may be designed as appropriate.

[0218] A PAPD graph, with radius on the horizontal axis and add power on the vertical axis, can be composed of one or more straight lines, one or more curved lines, or a combination of at least one straight line and one curved line. Each line can be represented by a linear equation, and each curved line can be represented by a polynomial. The polynomial equation is preferably of degree 4 to 8. However, higher degrees, such as 9 to 16, may be used if necessary. The straight line increases, decreases, or remains unchanged with increasing radius (in the radial direction from the center of the lens to the periphery of the lens). The curve may correspond to an increase, decrease, or an increase followed by a decrease, or a decrease followed by an increase, as the radius increases.

[0219] Subregions with NAPD may have NAPD graphs with different shapes. Figure 43 shows several examples of possible NAPD graphs in addition to the NAPD graphs shown in the previous figures of the EVR IOL of the present invention in this specification. Of course, other NAPD graph shapes not shown in this specification are also applicable to the EVR IOL of the present invention. In addition, the NAPD shapes shown in this specification may be modified as appropriate. In addition, NAPD graph shapes not shown in the figures of this specification may be designed as appropriate.

[0220] The NAPD graph, with radius on the horizontal axis and add power on the vertical axis, can be composed of one or more straight lines, one or more curved lines, or a combination of at least one straight line and one curved line. Each line can be represented by a linear equation, and each curved line can be represented by a polynomial. The polynomial equation is preferably of degree 4 to 8. However, higher degrees, such as 9 to 16, may be used if necessary. The straight line decreases or remains unchanged with increasing radius (in the radial direction from the center of the lens to the periphery of the lens). The curve may correspond to a decrease, an increase, a decrease followed by an increase, or an increase followed by a decrease with increasing radius.

[0221] For the EVR IOL of the present invention, the preferred average value of PAPD in a graph with radius on the horizontal axis and power on the vertical axis, or in a graph with radius on the horizontal axis and add power on the vertical axis, or within the lens when the sub-region having PAPD is viewed from the front (planar view), is 0.3D to 1.0D.

[0222] The preferred average power difference between the design power profile and the reference add power profile of the subregion having the ZAPD is between -0.2D and 0.2D. The preferred average value of the NAPD of the present invention is less than -0.3D. In other words, the preferred average absolute value of the NAPD is greater than 0.3D. This value of 0.3D takes into account that the power at the corneal surface is approximately 0.21D. This value of 0.21D at the corneal surface is very close to 0.25D, the minimum power interval in eyeglasses used for vision and visual field correction. In eyeglasses, 0.25D changes the visual acuity of the eyeglass wearer and the image quality of the objects viewed by the wearer. Therefore, setting the minimum PAPD value to 0.3D and the minimum absolute value of the NAPD to 0.3D can result in differences (improvements) in near vision correction and / or intermediate vision correction compared to when vision is corrected using a conventional IOL.

[0223] The area ratios of the subregions with PAPD, ZAPD, and NAPD in the lens region with the ADD power, when the total area of ​​the lens region with the ADD power is taken as 100%, are preferably within specific percentage ranges, which affect the optical properties and performance of the EVR IOL of the present invention for vision correction in the eye of a phakic patient.

[0224] The preferred area ratio of the sub-area with PAPD is 15% to 50% of the total area of ​​the near area with the add power. The preferred area ratio of the sub-area with ZAPD is 30% to 70%. The preferred area ratio of the sub-area with NAPD is 15% to 50%.

[0225] By maintaining the area ratio of the subregion with ZAPD at 30% to 60% of the total area of ​​the near region with add power, the near and / or intermediate distance ranges at which objects can still be seen clearly / distinctly in a phakic patient's eye implanted with an EVR IOL of the present invention can be maintained or remain equivalent to the near and / or intermediate distance ranges of prior art ("Flat") IOLs. The area ratio of the subregion with PAPD can improve near and / or intermediate vision, and the area ratio of the subregion with NAPD can improve distance vision.

[0226] The IOLs of the present invention can be made from a variety of IOL materials, including acrylic, silicone, PMMA, hydrogel, etc. They can be manufactured using a variety of known manufacturing processes, including lathing, casting / molding, printing, and combinations of different manufacturing processes.

[0227] In the ophthalmic lenses taught herein, the power profiles of the present invention and the optical designs of the present invention are also applicable to phakic IOLs (or implantable contact lenses) and EVR contact lenses.

[0228] The following describes aspects of the present invention. Aspect 1: The lens has at least one distance area for correcting vision for distance vision and at least one near area for correcting vision for near vision, the distance area being concentric with the lens center O; reducing the power in the distance region to at least partially offset the positive vertical spherical aberration of the average human cornea with a negative vertical spherical aberration; In the near area, a predetermined base power is provided at the lens center O, and a positive constant power is added to the aspherical base power within a predetermined radial range of the virtual aspherical lens so as to completely offset the positive vertical spherical aberration of the average human cornea; the near region comprises at least three radially aligned sub-regions; Subregion 1 provides a positive power deviation from the positive constant power, Subregion 2 provides a power deviation of approximately zero relative to the positive constant power; An intraocular lens, wherein subregion 3 provides a negative power deviation relative to the positive constant power. Aspect 2: A lens having a concentric region with a lens center O, the region including the lens center O and correcting visual acuity for near vision, and a far region disposed radially outward from the lens center O and correcting visual acuity for far vision, reducing the power in the distance region to at least partially offset the positive vertical spherical aberration of the average human cornea with a negative vertical spherical aberration; In the near area, a predetermined base power is provided at the lens center O, and a positive constant power is added to the aspherical base power within a predetermined radial range of the virtual aspherical lens so as to completely offset the positive vertical spherical aberration of the average human cornea; the near region comprises at least three radially aligned sub-regions; Subregion 1 provides a positive power deviation from the positive constant power, Subregion 2 provides a power deviation of approximately zero relative to the positive constant power; An intraocular lens, wherein subregion 3 provides a negative power deviation relative to the positive constant power. Aspect 3: A lens having a lens center O as a concentric region, the lens center O is included in the far region, and the far region corrects the visual acuity of far vision. The outer region is disposed radially outward from the lens center O and is positioned outside the near region, and corrects the visual acuity of far vision. in said outer region, reducing the power to at least partially offset the positive vertical spherical aberration of the average human cornea with a negative vertical spherical aberration; The near area has a predetermined base power at the lens center O, and adds a positive constant power to the aspherical base power within a predetermined radial range of the virtual aspherical lens so as to completely offset the positive vertical spherical aberration of the average human cornea; the near region comprises at least three radially aligned sub-regions; Subregion 1 provides a positive power deviation from the positive constant power, Subregion 2 provides a power deviation of approximately zero relative to the positive constant power; An intraocular lens, wherein subregion 3 provides a negative power deviation relative to the positive constant power. Aspect 4: The lens has at least one distance area for correcting vision for distance vision and at least one near area for correcting vision for near vision, the distance area being concentric with the lens center O; In the near area, a positive constant power is added to a reference power having a predetermined base power at the lens center O, the near region comprises at least three radially aligned sub-regions; Subregion 1 provides a positive power deviation from the positive constant power, Subregion 2 provides a power deviation of approximately zero relative to the positive constant power; An ophthalmic lens, wherein sub-region 3 provides a negative power deviation relative to said positive constant power. Aspect 5: With respect to the area of ​​the near region, The area ratio of the sub-region 1 is in the range of 15 to 50%, The area ratio of the sub-region 2 is in the range of 30 to 70%; The intraocular lens according to any one of aspects 1 to 3, wherein the area ratio of the subregions 3 is in the range of 15 to 50%. Aspect 6: the average value of the positive power deviation in the subregion 1 is in the range of 0.3 to 1 D, The average value of the approximately zero power deviation in the sub-region 2 is in the range of −0.2 to 0.2D, The intraocular lens according to any one of aspects 1 to 3, wherein the average value of the negative power deviation in the subregion 3 is in the range of −0.3D or less. Aspect 7: The intraocular lens according to any one of Aspects 1 to 3, wherein the positive constant power is in the range of 1 to 4D. Aspect 8: An intraocular lens according to any one of Aspects 1 to 3, wherein the subregions 1 to 3 are arranged in one of the following orders when viewed in the radial direction from the lens center O: Subarea 1, Subarea 2, Subarea 3 Subarea 1, Subarea 3, Subarea 2 Subarea 2, Subarea 1, Subarea 3 Subarea 2, Subarea 3, Subarea 1 Sub-area 3, Sub-area 1, Sub-area 2 Subarea 3, Subarea 2, Subarea 1. Aspect 9: With respect to the area of ​​the near region, The area ratio of the sub-region 1 is in the range of 15 to 50%, The area ratio of the sub-region 2 is in the range of 30 to 70%; 5. The ophthalmic lens according to aspect 4, wherein the area ratio of the sub-regions 3 is in the range of 15 to 50%. Aspect 10: the average value of the positive power deviation in the subregion 1 is in the range of 0.3 to 1 D, The average value of the approximately zero power deviation in the sub-region 2 is in the range of −0.2 to 0.2D, 5. The ophthalmic lens of claim 4, wherein the average negative power deviation in subregion 3 is in the range of −0.3D or less. Aspect 11: The ophthalmic lens according to Aspect 4, wherein the positive constant power is in the range of 1 to 4D. Aspect 12: The ophthalmic lens according to aspect 4, wherein the subregions 1 to 3 are arranged in one of the following orders when viewed in the radial direction from the lens center O: Subarea 1, Subarea 2, Subarea 3 Subarea 1, Subarea 3, Subarea 2 Subarea 2, Subarea 1, Subarea 3 Subarea 2, Subarea 3, Subarea 1 Sub-area 3, Sub-area 1, Sub-area 2 Subarea 3, Subarea 2, Subarea 1. Aspect 13: An intraocular lens as described in aspect 1 or 2, in which the change in power is smooth or abrupt, or the power jumps, at at least one of the boundaries between two different sub-regions, and the boundaries between each of sub-regions 1 to 3 and the far region when the near region and the far region are adjacent to each other. Aspect 14: An ophthalmic lens as described in Aspect 4, in which the change in power is smooth or abrupt, or the power jumps, at at least one of the boundaries between two different sub-regions, and the boundaries between the far region and each of the sub-regions 1 to 3 when the near region and the far region are adjacent to each other. Aspect 15: The intraocular lens according to Aspect 2, wherein the diameter of the near region in plan view is in the range of 1.2 to 2.5 mm. Aspect 16: An intraocular lens as described in Aspect 3, in which the change in power is smooth or abrupt, or the power jumps, at at least one of the boundaries between two different sub-regions, the boundaries between each of sub-regions 1 to 3 and the far region when the near region and the far region are adjacent, and the boundaries between each of sub-regions 1 to 3 and the far region when the near region and the outer region are adjacent. Aspect 17: The inner diameter of the near region in plan view is in the range of 1.4 to 2.2 mm, 4. The intraocular lens according to aspect 3, wherein the outer diameter of the near region in plan view is in the range of 2.6 to 3.5 mm. Aspect 18: The ophthalmic lens is a phakic intraocular lens; the near zone includes a lens center O; the far region is disposed outside the near region when viewed radially outward from a lens center O, 5. The ophthalmic lens according to aspect 4, wherein the diameter of the near region in plan view is in the range of 1.4 to 3 mm. Aspect 19: The ophthalmic lens is a phakic intraocular lens; the far region includes the lens center O; the near area is disposed outside the far area when the radial direction is taken outward from the lens center O, An outer region is disposed on the outer side of the near region when the radial direction from the lens center O is taken outward, and corrects vision for far vision, The inner diameter of the near region in a planar view is in the range of 1.6 to 2.4 mm, The ophthalmic lens according to aspect 4, wherein the outer diameter of the near region in plan view is in the range of 2.9 to 3.6 mm. Aspect 20: The ophthalmic lens is a contact lens; the near zone includes a lens center O; the far region is disposed outside the near region when viewed radially outward from a lens center O, The ophthalmic lens according to aspect 4, wherein the diameter of the near region in plan view is in the range of 1.4 to 3 mm. Aspect 21: The ophthalmic lens is a contact lens; the far region includes the lens center O; The near area is disposed outside the far area when viewed from the lens center O in the radial direction, An outer region is disposed on the outer side of the near region when the radial direction from the lens center O is taken outward, and corrects vision for far vision, The inner diameter of the near region in a planar view is in the range of 1.6 to 2.4 mm, 5. The ophthalmic lens according to aspect 4, wherein the outer diameter of the near region in plan view is in the range of 2.9 to 3.6 mm. Aspect 22: The intraocular lens according to any one of Aspects 1 to 3, wherein the intraocular lens is a toric lens. Aspect 23: A method for optically designing an intraocular lens according to any one of Aspects 1 to 3. Aspect 24: A method for manufacturing an intraocular lens, comprising manufacturing an intraocular lens designed by the optical design method described in aspect 23 using at least a lathe, molding, or 3D printing. Aspect 25: The ophthalmic lens of Aspect 4, wherein the intraocular lens is a toric lens. Aspect 26: A method for optically designing an ophthalmic lens according to aspect 4. Aspect 27: A method for manufacturing an ophthalmic lens, comprising manufacturing an ophthalmic lens designed by the optical design method described in aspect 26 using at least a lathe, molding, or 3D printing.

Claims

1. The lens has at least one distance zone for correcting vision for distance vision and at least one near zone for correcting vision for near vision, and the distance zone and the near zone are concentric with a lens center O; In the distance region, the optical power of the lens decreases as the radial distance to the lens center O increases; the near region comprises at least three radially aligned sub-regions; subregion 1 provides a positive power deviation to a virtual optical power profile in the near region, the virtual optical power profile being an aspheric power profile to which a positive constant power is added; Subregion 2 provides zero power deviation with respect to the virtual optical power profile; An intraocular lens, wherein subregion 3 provides a negative power deviation with respect to said virtual optical power profile.

2. 2. The intraocular lens of claim 1, wherein in the far region, the decrease in optical power with increasing radial distance to the lens center is such that the positive vertical spherical aberration of the human cornea, in particular the average human cornea, is at least partially offset.

3. 2. The intraocular lens according to claim 1, wherein the virtual optical power profile is such that the positive longitudinal spherical aberration of the human cornea, in particular of the average human cornea, is at least partially compensated for.

4. The lens has at least one distance area for correcting vision for distance vision and at least one near area for correcting vision for near vision, the distance area being concentric with the lens center O; reducing the power in the distance region to provide a negative longitudinal spherical aberration that at least partially offsets the positive longitudinal spherical aberration caused by the cornea; In the near area, a positive constant power is added to an aspherical reference power within a predetermined radial range of a virtual aspherical lens having a predetermined base power at the lens center O and completely canceling the positive vertical spherical aberration caused by the cornea, the near region comprises at least three radially aligned sub-regions; Subregion 1 provides a positive power deviation from the positive constant power, Subregion 2 provides a substantially zero power deviation with an average value of −0.2 to 0.2 D relative to the positive constant power; 2. The intraocular lens of claim 1, wherein the subregion 3 provides a negative power deviation relative to the positive constant power.

5. 2. The intraocular lens of claim 1, wherein the near zone includes the center O of the lens.

6. 2. The intraocular lens of claim 1, wherein the far region includes the lens center O, and the intraocular lens further comprises an outer region that is positioned radially outward from the lens center O more outward than the near region and that also corrects vision for distance, the far region, the near region and the outer region being concentric with the lens center O, and in the outer region, the optical power of the lens decreases as the radial distance to the lens center O increases.

7. 7. The intraocular lens according to claim 6, wherein in the outer region, the optical power of the lens decreases with increasing radial distance to the lens center O in order to at least partially offset the positive vertical spherical aberration of the human cornea, in particular the average human cornea, by negative vertical spherical aberration.

8. The lens has a lens center O as a concentric region, and the lens includes the lens center O and corrects vision for distance vision. The lens also has a near region that is located outside the far region when viewed radially outward from the lens center O and corrects vision for near vision. The lens also has an outer region that is located outside the near region and corrects vision for distance vision. the outer region is reduced in power to provide a negative longitudinal spherical aberration that at least partially offsets the positive longitudinal spherical aberration caused by the cornea; In the near area, a positive constant power is added to an aspherical reference power within a predetermined radial range of a virtual aspherical lens having a predetermined base power at the lens center O and completely canceling the positive vertical spherical aberration caused by the cornea, the near region comprises at least three radially aligned sub-regions; Subregion 1 provides a positive power deviation from the positive constant power, Subregion 2 provides a substantially zero power deviation with an average value of −0.2 to 0.2 D relative to the positive constant power; 2. The intraocular lens of claim 1, wherein the subregion 3 provides a negative power deviation relative to the positive constant power.

9. The lens has at least one distance zone for correcting vision for distance vision and at least one near zone for correcting vision for near vision, and the distance zone and the near zone are concentric with a lens center O; the near region comprises at least three radially aligned sub-regions; subregion 1 provides a positive power deviation to a virtual optical power profile in the near region, the virtual optical power profile being an aspheric power profile to which a positive constant power is added; Subregion 2 provides zero power deviation with respect to the virtual optical power profile; An ophthalmic lens, wherein subregion 3 provides a negative power deviation to said virtual optical power profile.

10. The lens has at least one distance area for correcting vision for distance vision and at least one near area for correcting vision for near vision, the distance area being concentric with the lens center O; In the near area, a positive constant power is added to a reference power having a predetermined base power at the lens center O, the near region comprises at least three radially aligned sub-regions; Subregion 1 provides a positive power deviation from the positive constant power, Subregion 2 provides a substantially zero power deviation with an average value of −0.2 to 0.2 D relative to the positive constant power; 10. An ophthalmic lens according to claim 9, wherein sub-region 3 provides a negative power deviation relative to said positive constant power.

11. With respect to the area of ​​the near region, The area ratio of the sub-region 1 is 15 to 50%; The area ratio of the sub-region 2 is 30 to 70%; The intraocular lens according to claim 4, wherein the area ratio of the sub-regions 3 is 15 to 50%.

12. the average value of the positive power deviation in the subregion 1 is 0.3 to 1 D; The intraocular lens according to claim 10, wherein the average value of the negative power deviation in the subregion 3 is −0.3D or less.

13. The intraocular lens of claim 1, wherein the positive constant power is 1 to 4D.

14. The intraocular lens according to claim 1, wherein the sub-regions 1 to 3 are arranged in one of the following orders when viewed in the radial direction from the lens center O. ・Sub area 1, sub area 2, sub area 3 ・Sub area 1, sub area 3, sub area 2 ・Sub area 2, sub area 1, sub area 3 ・Sub area 2, sub area 3, sub area 1 ・Sub area 3, sub area 1, sub area 2 ・Sub area 3, sub area 2, sub area 1

15. 2. The intraocular lens of claim 1, wherein the optical power changes continuously, discontinuously, or with a power jump at at least one of the boundary between two sub-regions of the near region and the boundary between the near region and the far region when the near region and the far region are adjacent.

16. The intraocular lens of claim 1, wherein the change in power is continuous or discontinuous, or the power jumps at at least one of the boundaries between different sub-regions within the near region, and the boundaries between any of the sub-regions 1 to 3 and the far region when the near region and the far region are adjacent to each other.

17. The intraocular lens according to claim 5, wherein the diameter of the near region in a plan view is 1.2 to 2.5 mm.

18. The intraocular lens of claim 6, wherein the change in power is continuous or discontinuous, or the power jumps at at least one of the boundaries between different sub-regions within the near region, the boundary between any of the sub-regions 1 to 3 and the far region when the near region and the far region are adjacent, and the boundary between any of the sub-regions 1 to 3 and the far region when the near region and the outer region are adjacent.

19. The intraocular lens according to claim 6, wherein the inner diameter of the near region in plan view is 1.4 to 2.2 mm, and the outer diameter is 2.6 to 3.5 mm.

20. the ophthalmic lens is a phakic intraocular lens; the near zone includes a lens center O; the far region is disposed outside the near region when the radial direction is taken outward from the lens center O, 10. The ophthalmic lens according to claim 9, wherein the diameter of the near region in plan view is 1.4 to 3 mm.

21. the ophthalmic lens is a phakic intraocular lens; the far region includes the lens center O; The near area is disposed outside the far area when viewed from a lens center O in a radial direction, an outer region disposed outside the near region and correcting vision for distance vision; 10. The ophthalmic lens according to claim 9, wherein the inner diameter of the near region in plan view is 1.6 to 2.4 mm, and the outer diameter is 2.9 to 3.6 mm.

22. the ophthalmic lens is a contact lens; the near zone includes a lens center O; the far region is disposed outside the near region when the radial direction is taken outward from the lens center O, 10. The ophthalmic lens according to claim 9, wherein the diameter of the near region in plan view is 1.4 to 3 mm.

23. the ophthalmic lens is a contact lens; the far region includes the lens center O; The near area is disposed outside the far area when viewed from a lens center O in a radial direction, an outer region disposed outside the near region and correcting vision for distance vision; 10. The ophthalmic lens according to claim 9, wherein the inner diameter of the near region in plan view is 1.6 to 2.4 mm, and the outer diameter is 2.9 to 3.6 mm.

24. The intraocular lens of claim 1 , wherein the intraocular lens is a toric lens.

25. 5. The intraocular lens of claim 4, wherein in subregion 1, the optical power decreases with increasing radial distance to the lens center O, the decrease in subregion 1 being concave, and in subregion 3, the optical power decreases with increasing radial distance to the lens center O, the decrease in subregion 3 being convex.

26. With respect to the area of ​​the near region, The area ratio of the sub-region 1 is 15 to 50%; The area ratio of the sub-region 2 is 30 to 70%; 10. The ophthalmic lens according to claim 9, wherein the area percentage of the sub-regions 3 is between 15 and 50%.

27. the average value of the positive power deviation in the subregion 1 is 0.3 to 1 D; The ophthalmic lens of claim 10, wherein the average value of the negative power deviation in the sub-region 3 is less than or equal to −0.3D.

28. 10. The ophthalmic lens of claim 9, wherein the positive constant power is between 1 and 4D.

29. 10. The ophthalmic lens according to claim 9, wherein the sub-regions 1 to 3 are arranged in one of the following orders when viewed in the radial direction from the lens center O: ・Sub area 1, sub area 2, sub area 3 ・Sub area 1, sub area 3, sub area 2 ・Sub area 2, sub area 1, sub area 3 ・Sub area 2, sub area 3, sub area 1 ・Sub area 3, sub area 1, sub area 2 ・Sub area 3, sub area 2, sub area 1

30. 10. The ophthalmic lens of claim 9, wherein the optical power changes continuously, discontinuously, or with a power jump at at least one of the boundary between two sub-regions of the near region and the boundary between the near region and the far region when the near region and the far region are adjacent.

31. 10. The ophthalmic lens according to claim 9, wherein the change in power is continuous or discontinuous, or the power jumps at at least one of the boundaries between different sub-regions within the near region, and the boundaries between any of the sub-regions 1 to 3 and the far region when the near region and the far region are adjacent to each other.

32. 10. The ophthalmic lens of claim 9, wherein in sub-region 1, the optical power decreases with increasing radial distance to the lens center O, the decrease in sub-region 1 being concave, and in sub-region 3, the optical power decreases with increasing radial distance to the lens center O, the decrease in sub-region 3 being convex.

33. An optical design method for designing an intraocular lens according to any one of claims 1 to 8, 11 to 19, 24 and 25, or an ophthalmic lens according to any one of claims 9, 10, 20 to 23 and 26 to 32.

34. Designing an aspheric power profile having an optical power that decreases as the distance to the center O of the lens to be designed increases; adding a positive constant power to a region of the designed aspheric power profile to design a near zone, wherein at least a portion of the designed aspheric power profile outside the near zone forms a far zone; changing the optical power in the near zone to design at least three subzones, wherein in subzone 1, the power is increased to design a positive power deviation for the designed aspheric power profile to which the positive constant power has been added, in subzone 2, the power is not changed to design a zero power deviation for the designed aspheric power profile to which the positive constant power has been added, and in subzone 3, the power is decreased to design a negative power deviation for the designed aspheric power profile to which the positive constant power has been added; 34. The optical design method of claim 33, comprising:

35. A method for manufacturing an intraocular lens, comprising manufacturing an intraocular lens or an ophthalmic lens designed by the optical design method according to claim 33 by at least one of lathing, molding, and 3D printing.

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