Ophthalmic lens with optical sectors

Abstract

An ophthalmic lens comprising a main lens part, a recessed part, an optical center, and an optical axis through the optical center. The main lens part has at least one boundary with the recessed part and has an optical power of between about −20 to about +35 diopter. The recessed part is positioned at a distance of less than 2 mm from the optical center and includes a near part having a relative diopter of about +1.0 to about +5.0 with respect to the optical power of the main lens part. The boundary or boundaries of the recessed lens part with the main lens part form a blending part or blending parts, are shaped to refract light away from the optical axis, and have a curvature resulting in a loss of light, within a circle with a diameter of 4 mm around the optical center, of less than about 15%.

Claims

1. An intra-ocular lens comprising opposing first and second sides, and a main lens part having a surface at the first side and an optical axis passing through an optical centre of the intra-ocular lens, the main lens part having an optical power; a recessed part having a surface at the first side, which surface is recessed with respect to the surface of the main lens part, the surface of the recessed part having at least one boundary with the surface of the main lens part and the recessed part comprising a near vision part, the near vision part having an add power with respect to the optical power of the main lens part; a central part having a surface at the first side, which surface is arranged such as to have boundaries with the surface of the main lens part and the surface of the recessed part, the central part having a relative optical power with respect to the optical power of the main lens part; wherein the central part is circular with a diameter between about 0.5 and 3.0 mm; and wherein the surface of the recessed part is shaped as a meridian zone having a boundary with the surface of the main lens part, the boundary comprising two semi meridians passing over the surface of the main lens part and through the optical centre.

2. The lens according to claim 1, wherein the central part comprises the optical centre.

3. The lens according to claim 1, wherein the relative optical power of the central part with respect to the optical power of the main lens part is between 0% and 100% of the relative optical power of the near vision part with respect to the optical power of the main lens part.

4. The lens according to claim 1, wherein the relative optical power of the central part is between about −2.0 and +2.0 dioptre with respect to the optical power of the main lens part.

5. The lens according to claim 1, wherein the central part is circular with a diameter between about 0.5 and 2.0 mm.

6. The lens according to claim 1, wherein the surface of the recessed part is bounded by a line of latitude, which is concentric with and at a distance from the central part in the radial direction with respect to the optical axis.

7. The lens according to claim 1, wherein the main lens part is configured for distance vision.

8. The lens according to claim 1, wherein the near vision part is configured for reading vision.

9. The lens according to claim 1, wherein the near vision part has a relative optical power of about +1.0 to about +5.0 dioptre with respect to the optical power of the main lens part.

10. The lens according to claim 1, wherein the near vision part has a relative optical power of about +1.5 to about +4.0 dioptre with respect to the optical power of the main lens part.

11. The lens according to claim 1, wherein the main lens part has an optical power of about −20 to about +35 dioptre.

12. The lens according to claim 1, wherein the main lens part has an optical power of about −10 to about +30 dioptre.

13. An intra-ocular lens comprising a main lens part having a curvature radius Rv; a circular central part having a first optical property and having a diameter between about 0.5 and 2 mm; and a meridian part comprising a recess which is bounded by the circular central part, by two meridians passing through a centre of the central part, and by a lower boundary which is concentric with respect to the circular part, the meridian part forming a recess in the lens, the recess having an outer limit lying on or within the curvature radius Rv, and the meridian part comprising a reading vision part.

14. An oculary supported multifocal intra-ocular lens provided with a circular central lens portion having a diameter between about 0.5 and 2 mm; a lower lens portion in a lower lens part of the multifocal lens neighbouring the central lens portion; and a further lens portion having a curvature radius Rv, wherein the lower lens portion comprises a recess comprising two sides which run from the central lens portion towards a rim of the multifocal lens, and an outer limit of the lower lens portion lies on or within an imaginary sphere having its origin and radius of curvature coinciding with the curvature radius Rv of the further lens portion.

15. The lens according to claim 1, wherein the central part is circular with a diameter between about 0.6 and 3.0 mm.

16. The lens according to claim 1, wherein the central part is circular with a diameter between about 0.8 and 3.0 mm.

17. The lens according to claim 1, wherein the central part is circular with a diameter between about 0.8 and 2.0 mm.

Description

DESCRIPTION OF EMBODIMENTS WITH REFERENCE TO THE DRAWINGS

(1) The invention will be further elucidated referring to embodiments of a Multifocal Sector Ophthalmic Lens, (MSOL) shown in the attached drawings, showing in:

(2) FIG. 1 a cross section of a human eye;

(3) FIG. 2 a cross section of a human eye with an IOL;

(4) FIG. 3 a front view of an embodiment of an MSIOL with an optical central part and a recessed part;

(5) FIG. 4 a side view of the MSIOL according to FIG. 3;

(6) FIG. 5 a cross sectional view over line IV of the MSIOL according to FIG. 3;

(7) FIG. 6 a detail of the cross section according to FIG. 5;

(8) FIG. 7 a perspective front side view of the MSIOL according to FIG. 3;

(9) FIG. 8 a perspective back side view of the MSIOL according to FIG. 3;

(10) FIG. 9 a front view of another embodiment of an MSIOL with a recessed part subdivided in three meridianally divided optical sectors and one central optical sector;

(11) FIG. 10 a side view of the MSIOL according to FIG. 9;

(12) FIG. 11 a perspective front side view of the MSIOL according to FIG. 9;

(13) FIG. 12 a front view of a further variant of the MSIOL with a recessed diffractive semi-meridian sector element;

(14) FIG. 13 a side view of the MSIOL according to FIG. 12;

(15) FIG. 14 a cross sectional view over line XIV of the MSIOL according to FIG. 12;

(16) FIG. 15 a detail of the cross section according to FIG. 14;

(17) FIG. 16 a perspective front side view of the MSIOL according to FIG. 12;

(18) FIG. 17 a comparison between a optimised transition trajectory and cosine trajectory of a transition or blend zone or part, illustrating that in the same time with the optimised profile a larger displacement is possible;

(19) FIG. 18 the sigmoid function without any scaling and translation on the interval [−10,10];

(20) FIG. 19 the experienced or effective acceleration (second derivative) during the sigmoid transition;

(21) FIG. 20 the reduction of the transition zone width by calculating the needed transition time and distance according the method described in this document locally, the transition zone width is zero near the centre;

(22) FIGS. 21-26 graphs showing the energy distribution in various parts of several embodiments of ophthalmic lenses;

(23) FIGS. 27-29 measured data of ophthalmic lenses;

(24) FIGS. 30-32 graphs of steepness's of blending or transition zones or parts;

(25) FIGS. 33 and 34 test results showing the LogCS against the spatial frequency;

(26) FIG. 35 showing a surface model of one of the embodiments;

(27) FIG. 36 a schematic setup of measuring instrument PMTF.

DETAILED DESCRIPTION OF EMBODIMENTS

(28) A preferred embodiment of the invention is now described in detail. Referring to the drawings, like numbers indicate like parts throughout the views. As used in the description herein and throughout the claims, the following terms take the meanings explicitly associated herein, unless the context clearly dictates otherwise: the meaning of “a,” “an,” and “the” includes plural reference, the meaning of “in” includes “in” and “on.” Unless defined otherwise, all technical and scientific terms used herein have the same meanings as commonly understood by one of ordinary skilled in the art to which this invention belongs. Generally, the nomenclature used herein and the laboratory procedures are well known and commonly employed in the art. Conventional methods are used for these procedures, such as those provided in the art and various general references.

(29) It should be understood that the anterior optical sectors are preferably concentric with the geometric centre of the posterior surface

(30) A “vertical meridian” refers to an imaginary line running vertically from the top, through the centre, to the bottom of the anterior surface of an MSIOL when said MSIOL is maintained at a predetermined orientation into the eye

(31) A “horizontal meridian” refers to an imaginary line running horizontally from the left side, through the centre, to the right side of the anterior surface of an MSIOL when said MSIOL is maintained at a predetermined orientation into the eye. The horizontal and vertical meridians are perpendicular to each other.

(32) “Surface patches” refer to combinations of curvatures and lines that are continuous in first derivative, preferably in second derivative, from each other.

(33) A “outer boundary”, in reference to a zone other than a central optical zone on the surface of an MSIOL, refers to one of two peripheral boundaries of that zone which is further away from the geometric centre of the anterior surface.

(34) An “inner boundary”, in reference to a zone other than a central optical zone on the surface of an MSIOL, refers to one of two peripheral boundaries of that zone which is closer to the geometric centre of the anterior surface.

(35) A “semi-meridian” refers to an imaginary line running radially from the geometric centre of the anterior surface of an MSIOL to the edge of the lens.

(36) The “upper portion of the vertical meridian” refers to one half vertical meridian that is above the geometric centre of the anterior surface of an MSIOL, when said lens is maintained at a predetermined orientation inside an eye.

(37) The “lower portion of the vertical meridian” refers to one half vertical meridian that is below the geometric centre of the anterior surface of an MSIOL, when said lens is maintained at a predetermined orientation inside an eye.

(38) A “continuous transition”, in reference to two or more sector, means that the slope of these sectors are continuous at least in first derivative, preferably in second derivative.

(39) A “vertical meridian plane” refers to a plane that cuts through the optical axis of an MSIOL and a vertical meridian on the anterior surface of the MSIOL.

(40) As used herein in reference to the sectors or parts of an MSIOL the terms “Baseline Power”, “optical power”, “Add Power” and “Dioptre power” refer to the effective optical or Dioptre power of a sector when the lens is part of an ocular lens system such as for instance a cornea, a MSIOL, a retina and the material surrounding these components. This definition may include the effects of the divergence or angle of light rays intersecting the MSIOL surface caused by power of the cornea. In certain instances, an algorithm for calculating the Dioptre power may begin with a ray-tracing model of the human eye incorporating a subdivided sector MSIOL. At a particular radial location on the MSIOL surface Snell's law may be applied to calculate the angle of the light ray following the refraction. The optical path length of the distance between a point on the surface and the optical axis (axis of symmetry) may be used to define the local radius of curvature of the local wave front. Using such an approach, the Dioptre power is equal to the difference in indices of refraction divide by this local radius of curvature.

(41) The present invention aims to improve ophthalmic lenses, and in one aspect relates to an novel Multifocal Sector Intra Ocular Lens (MSIOL) with at least two semi-meridian optical sectors where at least one of the semi-meridian optical sectors is radial or angular subdivided and could comprise an inner sector, an intermediate sector, and an outer sector, located within the (imaginary) boundary of the distance part. The inner sector has a first optical power, the intermediate sector adjacent to the first optical power has a second optical power. The outer sector adjacent to the second optical power has a third optical power whereas the step height between the boundaries of the semi-meridian sectors are joint by means of a optimised transition profile to maximize light energy directed to the macula and to reduce blur and halo's at bigger pupil size. The ophthalmic lens semi-meridian sectors could have a continuous power profile or the discrete optical sub circle sectors blend together or combinations thereof. The subdivided sector(s) will provide a clear vision at reading and intermediate distances. Whereas the distance vision and contrast sensitivity remain comparable with an mono focal ophthalmic lens with reduced blur and halo's at bigger pupil size. The present invention may also be configured to perform well across eyes with different corneal aberrations (e.g., different asphericities), including the spherical aberration, over a range of decentration.

(42) The ophthalmic lens may be designed to have a nominal optical power for distance vision, defined as “Baseline Power”, usually of the main lens part, an “Add power” added on top of the nominal optical power or Baseline power, and intended for the reading vision. Often, also an intermediate optical power is defined suited for the particular environment in which it is to be used. In case of an MSIOL, is anticipated that the nominal optical power or baseline power of an MSIOL will generally within a range of about −20 Dioptre to at least about +35 Dioptre. The “Add power” will generally be in a range of about +1 Dioptres to at least about +5 Dioptre. Desirably, the nominal optical power of the MSIOL is between about 10 Dioptres to at least about 30 Dioptre, the “Add power” will be between about +1.50 and +4.00 Dioptre. In certain applications, the nominal optical power of the MSIOL is approximately +20 Dioptre, and the Add power about +3.00 Dioptre, which is a typical optical power necessary to replace the natural crystalline lens in a human eye.

(43) In FIG. 1, a schematic view of a human eye 100 with its natural lens 106 is shown. The eye has a vitreous body 101 and cornea 102. The eye has an anterior chamber 103, iris 104 and ciliary muscle 105 which hold the lens. The eye has a posterior chamber 107. In FIG. 2, the eye 100 is shown with an intra ocular lens 1 replacing the original lens 106.

(44) In FIG. 3, an embodiment of an intra ocular lens (IOL) 1 is shown which has haptics 2 and a lens zone or lens part 3. The lens part 3 is the actual optically active part of the IOL 1. The haptics 2 can have a different shape. In this embodiment, lens part 3 has a central part 6 which is usually substantially circular. It may deviate a little from an absolute circle, but in most embodiments it is as round or circular as possible in the specific further lens design. The lens part 3 further has a meridian part in a recess area. This recess is below the surface of the curved surface of the remaining lens part 4 of lens part 3. In other words, the curved surface of the remaining lens part 4 has a radius of curvature Rv, and the recess of the meridian part lies on or within the curvature radius Rv (see FIG. 4). It should be clear that curved surface of the lens part can be non-spherical or aspheric. In fact, the curved surface can be as described in for instance U.S. Pat. No. 7,004,585 in columns 6, 7 and 8. In particular the Zernike polynomials can be used to describe any curved surface of an ophthalmic lens.

(45) In this embodiment, the meridian part is divided into two concentric sub-zones 7 and 8.

(46) The various parts, i.e. the central part 6, inner meridian part 7 And outer meridian part 8, each have a have an angle of refraction or power which differs from the remaining lens part 4. When the lens part 3 is considered as part of a sphere having an axis through the crossing of lines R and S, then the central part 6 can also be defined as bounded by a first line of latitude. In this definition, sub-zone 7 can be defined as bounded by two meridians, the first line of latitude and a second line of latitude. Following this same definition, sub-zone 8 can be defined as bounded by the two meridians, the second line of latitude and a third line of latitude. In most embodiments, the meridian part (in cartography an area of this shape is also referred to as “longitudinal zone”) is referred to as a “reading part”.

(47) The MSIOL comprises a near part or reading part which is bounded on or within the lens zone 3 whereas the transition between those parts is performed with a cosine function or sigmoid function, but desirably joined with the optimized transition function discussed below. In general terms, these general transitions curves are referred to as S-shaped curves. These transitions have a width and are referred to as blending zone or transition zone.

(48) The near or reading part in an embodiment has an included angle α between about 160 and 200 degrees. In a further embodiment, the included angle is between about 175 and 195 degrees. The reading part can optically be sub divided into at least two imaginary circle sectors 7 and 8, forming a continuous transition surface radial about the optical axis or geometric axis. The required shape (and curvature of the recessed surface) of those circle sectors 7, 8 can be calculated using ray tracing to control at least the amount of spherical aberration and further to avoid image jumps. The reference lines in the lens part 3 are imaginary and for dimensional reference purpose. They are, however, not visible in the real product.

(49) The lens part 3 in this embodiment has an outer diameter between about 5.5 and about 7 mm. In a preferred embodiment, it is about 5.8-6.2 mm. The central part or inner sector 6 has a optical power at least equal to the baseline power. Desirably, the optical power of the inner circle sector or central part 6 is between 0% and 100% of the Add power.

(50) The central part 6 in an embodiment has a diameter of between about 0.2 mm and 2.0 mm. In an embodiment, the diameter of the central part 6 is between about 0.60 and 1.20 mm. In case the central part 6 is not absolutely round, it is a circumscribing circle having the diameter range mentioned here.

(51) Circle Sector or central part 6 has a optical power at least equal to the baseline power. In this embodiment, the recessed part has two indicated subzones, a first subzone 7 near the central part 6. This inner subzone has a latitude radius of between about 1.5 and 2.3 mm. In an embodiment, it is between about 1.8 and 2.1 mm. The outer subzone 8 has an optical power equal or greater than the baseline power. In an embodiment, the optical power is between 0 and 100% of the Add power. Thus, it forms an intermediate between the main lens part or the central part, and a near part in outer subzone 8. The latitude radius of outer subzone 8 has a dimension between about 2.2 and 2.7 mm. In an embodiment, it can be between about 2.3 and 2.6 mm. In this embodiment, the main lens part almost continues at part 9. The outer limit radius where the lens main lens part 4 continues can have a latitude radius of between about 2.6 and 2.8 mm. In an alternative embodiment, several concentric subzones can be provided in order for the recessed part to disturb or influence the central part for distance vision as little as possible.

(52) The IOL 1 has two semi meridian blending zones or blending parts 10 bounding the recessed part 7, 8. These semi meridians bounding blending parts 10 have an angle γ. In an embodiment, the angle will be less than 35°. In an embodiment, it will be less than 17°. In particular, the angle γ will be less than 5°. Usually, it will be more than about 1°.

(53) The recessed part in this embodiment further has a blending zone 11 which is concentric with respect to the optical axis R. Main lens part 4 continues in the concentric region indicated with reference number 9.

(54) In FIGS. 9-11, several view of another example of an ophthalmic lens is shown, as an Intra ocular lens. In this embodiment, again the recessed part is divided into subzones. Here, the two outer subzones 7 are angularly arranged at both sides of a central subzone 8′. The MSIOL comprises a main lens part 4 with a recessed part with a total included angle α between 160 and 200 degrees, desirably between 175 and 195 degrees. The included angle of the outer subzones 7 is between about 10 and 30 degrees. In an embodiment, it is between about 15 and 25 degrees. The included angle β of the central subzone 8′ is between about 80 and 120 degrees. In an embodiment, the central subzone 8′ is between 85 and 100 degrees.

(55) The total included angle of the subzones 7, 8′ for near and intermediate vision are bounded by the main lens part 4. The transitions or blend zones between the various parts follow a cosine function or sigmoid function. In an embodiment, they follow an optimized transition function described below. Due to this optimized transition profile at least one of those imaginary transition lines will be curved.

(56) The subzones 7 and 8′ are radial arranged around the geometric axis. The optical shape of those circle parts are ray traced to control the amount of spherical aberration and further to avoid image jumps. The reference lines in the lens parts are imaginary and for dimensional reference purpose only and are not visible in the real product. The lens part has a outer diameter dimension between 5.5 and 7 mm. In an embodiment, the diameter is about 6 mm. The central part 6 has a optical power at least equal to the baseline power of the main lens part. The diameter of central part has a diameter of between about 0.2 mm and 2.0 mm. In an embodiment, the diameter is between about 0.40 and 1.20 mm. The recessed part can have a radial width of between about 1.5 and 2.3 mm. In an embodiment, the width is between about 1.8 and 2.1 mm. In an embodiment, the outer subzones 7 have a optical power of about 30 to 60% of the Add power, i.e. about 30-60% of the relative dioptre of the central part 8′.

(57) The MSIOL as shown in FIGS. 3-8 may also be used in conjunction with another optical device such as a Diffractive Optical Element (DOE) 20. In an embodiment shown in FIGS. 12-16, such an embodiment is shown. That MSIOL comprises a recessed lens part 7 shaped as a refractive semi-meridian part having a first optical power. The total included angle γ of the recessed part can be between about 160-200 degrees. In an embodiment, the enclosed angle is between about 175-195 degrees. The diffractive optical element 20 is superposed on the surface of the recessed part 7. It is shown in an exaggerated way with larger scaled features. In practice, the features of the diffractive optical element 20 can be around about 0.5-2 micron in size. In an embodiment, the diffractive optical element 20 can be provided in the outer radial part of the recessed part 7. Thus, the central part 6 can have the same optical power or differ only up to about 1 dioptre with respect to the main lens part 4. The first subzone of the recessed part 7 can differ 0.5-2 dioptre with respect to the central part 6.

(58) The refractive reading part as described in FIGS. 3-8 may have an additional DOE element to correct for chromatic aberration or to further improve the distance and reading performance of the MSIOL. This is depicted in FIGS. 12-16. The DOE part 20 may be ray traced to control the amount of spherical aberration and further to reduce halo's and glare. The lens zone 3 also has a outer diameter of between about 5.5 to 7 mm. In an embodiment, it is about 5.8-6.2 mm. The central part 6 has a optical power at least equal to the baseline optical power of remaining lens part 4. Desirably, the optical power of the inner circle sector 7 is between 0% and 100% of the Add power. The embedded semi-meridian circle sector used as the refractive base for the DOE 20 has a optical power 10% and 100% of the Add power. The recessed part has a width (from the end of the central zone to blending past 11) between 1.5 and 2.3 mm. In an embodiment, it is between 1.8 and 2.1 mm. The DOE 20 may be configured for the baseline power and the intermediate Add power.

(59) In an embodiment, transition zones or blend zones 10 bounding the recessed part of the embodiments described in FIGS. 3-16 can follow a cosine function or a sigmoid function. In an embodiment, the transition zones 10 follow an optimized transition function described below. The transition or blending zones 13 and 13′ can also follow such a function.

EXAMPLES

(60) Several lens configurations based on FIGS. 3-8 are presented below, for an IOL. For several pupil diameters, the area covered in mm.sup.2 by the various sectors (zones or regions) are shown. In several graphs, the theoretically determined, relative light energy based on the area covered by the various sectors is shown. (Sector Radius Central refers to the radius of the central part). These theoretical example calculation were done as if the lens has no radius of curvature, i.e. a flat surface. This method has been chosen to simplify the calculation because the curvature of the lens surface will change with the optical power. The equations for calculating the surface area of a transition area used in the embodiments below are as follows.

(61) $A_{\mathrm{Pupil}}=\frac{\pi }{4}{D}_{\mathrm{pupil}}^2$$A_{\mathrm{Near}}=\frac{{\alpha }_{\mathrm{near}}.Math.\pi }{360.Math.4}\left(D_{\mathrm{pupil}}^2-D_{\mathrm{dist}}^2\right)$$A_{\mathrm{Dist}}=\frac{{\alpha }_{\mathrm{far}}.Math.\pi }{360.Math.4}\left(D_{\mathrm{pupil}}^2-D_{\mathrm{dist}}^2\right)+\frac{\pi }{4}{D}_{\mathrm{dist}}^2$$A_{\mathrm{Transition}}=\frac{{\alpha }_{\mathrm{trans}}.Math.\pi }{360.Math.4}\left(D_{\mathrm{pupil}}^2-D_{\mathrm{dist}}^2\right)$

(62) It was found that these values can also be determined using measurements. To that end, an instrument called PMTF can be used. This instrument is available from Lambda-X SA, Rue de l'industrie 37, 1400 Nivelles, BELGIUM. In the measurement procedure, an IOL is placed in an ISO model eye. A schematic drawing of the principle of PMFT is shown in FIG. 36, showing a light source 380, a target 381 for providing a spacially defined light area, a collimating lens 382, an aperture 383, a set of lenses L1 and L2, An ISO eye model 384 holding the IOL in a cuvette, a microscope 385 on a translation table 386 and a CCD camera 387 mounted on said microscope 385. In the measurements used below, the eye model has a 4 mm diameter aperture for simulating the pupil.

(63) The measurement procedure and data handling were as follow. The order of measurements of the IOLs can be reversed. In the measurements, an IOL with only one optical zone is measured, and the same IOL but with an optical zone according to the invention is measured using the same procedure.

(64) The measurements are performed according to the normal use of the PMFT. In this case, first a reference IOL without recessed part was measured. In the focal plane the light within an image of the aperture was measured by integrating the calibrated intensity on the CCD sensor. Next, an IOL with recessed part was measured. To that end, first the different focal planes of the IOL and the focal plane of the reference IOL are located. The intensity was measured in the focal planes of the IOLs. Thus, in case of an IOL with a far region (the main lens part) and a near region in the recessed part, the light in two focal planes was measured. From the light measurements on the CCD camera, the light in the focal planes was added and compared to the light in the focal plane of the reference IOL. The measured values for light loss corresponded very well with theoretically calculated light loss.

(65) Embodiment 1, FIG. 24

(66) TABLE-US-00002 Sector Angle Distance 182 Sector Angle Near 170 Sector Angle Transitions 8 each recess 4 degrees transition Sector Radius Central 0.57 Pupil 4.00 4.00 3.50 3.50 3.00 3.00 2.50 2.50 2.00 2.00 1.50 1.50 1.14 1.14 diameter Area 12.57 9.62 7.07 4.91 3.14 1.77 1.02 Pupil Area near 5.45 43% 4.06 42% 2.86 40% 1.84 37% 1.00 32% 0.35 20% 0.00 0% sector Area dist 6.86 55% 5.37 56% 4.08 58% 2.99 61% 2.09 67% 1.40 79% 1.02 100%  sector Area 0.26 2.0%  0.19 2.0%  0.13 1.9%  0.09 1.8% 0.05 1.5%  0.02 0.9%  0.00 0% transition
Embodiment 2, FIG. 25

(67) TABLE-US-00003 Sector Angle Distance 170 Sector Angle Near 160 Sector Angle Transitions 30 each recess 15 degrees transition Sector Radius Central 0.57 Pupil 4.00 4.00 3.50 3.50 3.00 3.00 2.50 2.50 2.00 2.00 1.50 1.50 1.14 1.14 diameter Area 12.57 9.62 7.07 4.91 3.14 1.77 1.02 Pupil Area near 5.13 41% 3.82 40% 2.69 38% 1.73 35% 0.94 30% 0.33 19% 0.00 0% sector Area dist 6.47 52% 5.08 53% 3.88 55% 2.86 58% 2.02 64% 1.37 78% 1.02 100%  sector Area 0.96 7.7%  0.72 7.4%  0.50 7.1%  0.32 6.6%  0.18 5.6%  0.06 3.5%  0.00 0% transition

(68) The IOL was also available without recessed part. This IOL was used as reference lens. It has a dioptre of +20 for the main lens part. The lens of the invention was further identical, except that it had a recessed part with a relative dioptre of +3 with respect to the main lens part. The measurement procedure above using the PMTF was used. In the table, results using a spatially “large” circular source of 600 mu diameter and a “small” source of 200 mu diameter are shown.

(69) TABLE-US-00004 Source Small Large Small Large Small large Pupil 4.5 4.5 3.75 3.75 3.00 3.00 diameter Light in 54% 58% 54% 54% 54% 54% far focus Light in 40% 34% 38% 38% 38% 41% near focus Area  6%  7%  8%  8%  8%  6% transition

(70) The measured results and calculated results thus are comparable.

(71) Embodiment 3, FIG. 26

(72) TABLE-US-00005 Sector Angle Distance 182 Sector Angle Near 170 Sector Angle Transitions 8 each recess 4 degrees transition Sector Radius Central 0.25 Pupil 4.00 4.00 3.50 3.50 3.00 3.00 2.50 2.50 2.00 2.00 1.50 1.50 0.50 0.50 diameter Area 12.57 9.62 7.07 4.91 3.14 1.77 0.20 Pupil Area near 5.84 46% 4.45 46% 3.25 46% 2.23 45% 1.39 44% 0.74 42% 0.00 0% sector Area dist 6.45 51% 4.96 52% 3.67 52% 2.58 53% 1.69 54% 0.99 56% 0.20 100%  sector Area 0.27 2.2% 0.21 2.2%  0.15 2.2%  0.10 2.1%  0.07 2.1%  0.03 2.0%  0.00 0% transition
Embodiment 4, FIG. 23

(73) TABLE-US-00006 Sector Angle Distance 145 Sector Angle Near 145 Sector Angle Transitions 70 each recess 35 degrees transition Sector Radius Central 1 Pupil 4.00 4.00 3.50 3.50 3.00 3.00 2.50 2.50 2.00 2.00 diameter Area 12.57 9.62 7.07 4.91 3.14 Pupil Area near 3.80 30% 2.61 27% 1.58 22% 0.71 15% 0.00  0% sector Area dist 6.94 55% 5.75 60% 4.72 67% 3.85 79% 3.14 100% sector Area 1.83 14.6%   1.26 13.1%   0.76 10.8%   0.34 7.0%  0.00  0.0% transition
Embodiment 5, FIG. 22

(74) TABLE-US-00007 Sector Angle Distance 145 Sector Angle Near 145 Sector Angle Transitions 70 each recess 35 degrees transition Sector Radius Central 0.00 Pupil 4.00 4.00 3.50 3.50 3.00 3.00 2.50 2.50 2.00 2.00 1.50 1.50 0.00 0.00 diameter Area 12.57 9.62 7.07 4.91 3.14 1.77 0.00 Pupil Area near 5.06 40% 3.88 40% 2.85 40% 1.98 40% 1.27 40% 0.71 40% 0.00 0% sector Area dist 5.06 40% 3.88 40% 2.85 40% 1.98 40% 1.27 40% 0.71 40% 0.00 100%  sector Area 2.44 19.4%   1.87 19.4%   1.37 19.4%   0.95 19.4%   0.61 19.4%   0.34 19.4%   0.00 0% transition

(75) For embodiment 2, measurements were made in an Optocraft optical bench according to ISO 11979-2. In FIGS. 27-29 measurements are shown of devices having a main lens part with an optical power of +22 (FIG. 27), +29 (FIG. 28) and +15 (FIG. 29). The recessed part has a near vision part having a relative optical power (with respect to the main part) of +3.0. All the examples relate to an IOL with varying optical power of the main part. In FIG. 27, the half right below is recessed. In FIG. 28, the recessed part is upper-left, in FIG. 29, the recess is the left side. The scale is Wave-front/lambda=0.54 micron. In FIG. 27 the total scale is from −10.6 to 4.6, in FIG. 28 the scale is about −6.8 to 8.8, in FIG. 29 the scale is −12.4 to 6.3. The usual colour scale was converted to greyscale.

(76) When manufacturing a MSIOL of the type described in this document by turning, the material removing tool usually moves parallel to the rotational axis away from and towards the work piece in a synchronised way with the angle of rotation. In this way a semi-meridian reading sector 7, 8′, 20 can be created embedded or recessed in the main lens part 4. When the transition 10 is made from main lens part 4 into recessed part 7, 8 the tool and the work piece or lens have to be moved towards each other. When the transition 10 is made out of the recessed part 7, 8 to the main lens part 4, the tool and the lens have to move away from each other. When manufactured this way, a transition zone 10, 13, 13′ separates the recessed part(s) from the main lens part 4. It should be clear that the dimensions of this transition zone should be as small as possible. It was found that the best results are provided if the transition zones are as small or narrow and thus as steep as possible.

(77) To make the smallest transition zone the cutting tool and the lens should be moved towards each other and away from each other as fast as possible. Often, the tool will move with respect to the lens. Fast displacement implies the tool should be moved with the fastest acceleration allowed by the manufacturer of the cutting tool or capable by the cutting tool. The method of the present invention calculates the optimal transition profile to move the cutting tool from position 1 at rest to position 2 at rest. Position 1 corresponds to the z position of the cutting tool when processing the distance part, and position 2 corresponds to the position of the cutting tool when processing the reading part or vice versa.

(78) If the movement of the cutting tool is limited by a specified maximum acceleration, then the fastest transition between two positions is accomplished by performing the displacement of the fast tool with this maximum acceleration during the whole transition. From simple mechanics it follows that the displacement s after applying the maximum acceleration a.sub.max during a time t.sub.1 is:
s=½a.sub.maxt.sub.1.sup.2

(79) The cutting tool will now have a speed of:
v=a.sub.maxt.sub.1

(80) To bring the fast tool back to rest v=0 we apply again the maximum acceleration on the fast tool system but now in the opposite direction. From simple mechanics it follows that the time needed to stop the fast tool t.sub.2 is equal to the time that was needed to accelerate the fast tool.
t.sub.2=t.sub.1

(81) When the transition time is Δt half of the transition time is needed to accelerate the fast tool and half of the transition time is needed to bring the fast tool at rest again. From this the optimised profile that utilises the maximum allowed acceleration for the tool is given by:

(82) $s\left(t\right)=\frac{1}{2}{a}_{\max }{t}^2$$\mathrm{For}0\le t<\frac{\Delta t}{2}$$s\left(t\right)=\frac{1}{2}{a_{\max }\left(\frac{\Delta t}{2}\right)}^2+a_{\max }\frac{\Delta t}{2}\left(t-\frac{\Delta t}{2}\right)-\frac{1}{2}{a_{\max }\left(t-\frac{\Delta t}{2}\right)}^2$$\mathrm{For}\frac{\Delta t}{2}\le t\le \Delta t$

(83) Where Δt is the transition time.

(84) The total and maximum displacement Δs when limited to the maximum acceleration a.sub.max of the fast tool is:

(85) $\Delta s={a_{\max }\left(\frac{\Delta t}{2}\right)}^2$

(86) The minimum time needed to make a displacement Δs is:

(87) $\Delta t=2\sqrt{\frac{\Delta s}{a_{\max }}}$

(88) This time is the theoretical minimal time to make a displacement Δs with the cutting tool that is limited to a maximum acceleration. All other transition profiles subjected to the same limitation regarding the maximum acceleration require a larger time to make the same displacement Δs.

(89) An important fact is that in practice to achieve a surface manufactured by turning of good quality the spindle speed is bounded to a minimum number of revolutions per minute. If the spindle speed is bounded to a minimum a smaller transition time will result in a smaller transition zone. The angular size φ in degrees of the transition zone in this case can be calculated by:

(90) $\varphi =N.Math.360.Math.\Delta t$$\varphi =N.Math.360.Math.2\sqrt{\frac{\Delta s}{a_{\max }}}$
with N the spindle speed in revolutions per second.

(91) Generally the height difference between the reading part and distance part decrease when moving from the periphery toward the centre of the optical zone. This implies that the angular size of the transition zone can be made smaller when approaching the centre. In this way the effective area of the optical zones is maximised. Another important advantage is that the transition is made as steep as possible this way. A steep transition can be advantageous, reflections at the transition zone are in such a way they are less or not perceived as disturbing by the patient. From this it can be concluded that with the optimised transition profile a larger displacement can be achieved for the same size of the transition profile. Or otherwise when certain amount of displacement is needed to change from distance part to reading part with the optimised transition profile this can be achieved in a faster way resulting in a smaller transition zone. A further application for the described optimised transition profile is this. To make a displacement Δs in a time Δt in the most controlled or accurate way it can be advantageous to make the transition with the minimum acceleration. The minimum acceleration needed to achieve a displacement Δs in a time Δt can be calculated with:

(92) $a_{\min }=\frac{4\Delta s}{\Delta t^2}$

(93) The transition profile is given again by:

(94) $s\left(t\right)=\frac{1}{2}a{t}^2$$\mathrm{For}0\le t<\frac{\Delta t}{2}$$s\left(t\right)=\frac{1}{2}{a\left(\frac{\Delta t}{2}\right)}^2+a\frac{\Delta t}{2}\left(t-\frac{\Delta t}{2}\right)-\frac{1}{2}{a\left(t-\frac{\Delta t}{2}\right)}^2$$\mathrm{For}\frac{\Delta t}{2}\le t\le \Delta t$

(95) Where Δt is the transition time and a is the maximum acceleration or a specified acceleration for the most controlled transition. The above described transition starts with a horizontal slope and ends with a horizontal slope. For the case that both near and reading part zone are rotational symmetric surfaces both zones have horizontal slopes in the tangential or tool direction. In this case the zones can be connected by the transition profile in a smooth way with no discontinuity in the first derivative. In case one or both zones has or have for example non rational symmetric surfaces such as a toric surface or a decentred spherical surface, the slope will generally not be horizontal in the tool direction. To make a smooth transition in case one of the zones does not have a horizontal or zero slope in the tangential direction, the transition can be made by removing some part of the beginning or the end of the transition profile in such a way that both zones and transition zone become tangent at their point of connection. See FIG. 17. It's also not difficult to do the same analysis as above in a more generally way. That is the assumption that the tool is at rest in position 1 and in position 2 is dropped. Instead, the tool is allowed to start with a specified velocity v1 before the transition and remains at a speed v2 after the transition. The last resulting in transition profile that does optional not start or end with a horizontal slope.

(96) Of course if one chooses it's also possible to start the transition without being tangent with one or both optical zones.

Example 1

(97) Maximum acceleration for the cutting tool:
a.sub.max=10 m/sec.sup.2

(98) Spindle speed 1200 rev/min (20 rev/sec) with a transition angle of 20 degrees.

(99) $\Delta t=\frac{1}{20}\frac{20}{360}=2.78.Math.{10}^{-3}\sec$$\frac{\Delta t}{2}=1.39.Math.{10}^{-3}\sec$

(100) For 0≦t<1.39.Math.10.sup.−3: s(t)=5t.sup.2

(101) For 1.39.Math.10.sup.−3≦t<2.78.Math.10.sup.−3:

(102) s(t)=9.66.Math.10.sup.−6+1.3.9.Math.10.sup.−3(t−1.39.Math.10.sup.−3)−5(t−1.39.Math.10.sup.−3).sup.2

Example 2

(103) Spindle speed N=15 rev/sec. Δs=0.05 mm, a.sub.max=10 m/sec.sup.2

(104) $\Delta t=2\sqrt{\frac{\Delta s}{a_{\max }}}=0.0045\sec$$\varphi =N.Math.360.Math.2\sqrt{\frac{\Delta s}{a_{\max }}}=15*360*0.0045=24\mathrm{degrees}$

(105) It's also possible to make the transition by using other less optimal profiles. For example a transition profile described by the cosine function could be used.
s(t)=A.Math.cos(ωt)

(106) With A the amplitude and ω the angular frequency. The transition starts at ω=0 and ends at ω=π. The acceleration experienced when following this cosine profile is:
a=−A.Math.ω.sup.2 cos(ωt)

(107) The maximum acceleration in the cosine profile will occur at ω=0 and at ω=π in the opposite direction. The absolute magnitude of the acceleration is therefore:
a.sub.cos.sub._.sub.max=A.Math.ω.sup.2

(108) Because the maximum acceleration available or allowed for the turning machine is only used during a very small trajectory in the transition profile, the achieved displacement for the fast tool is substantially less than the described optimal transition profile in this document.

(109) For comparison purposes, a cosine transition is calculated with the same transition time and maximum acceleration as used in the example above with the optimised transition profile (FIG. 17).

(110) The angular frequency ω can be calculated from the transition time:

(111) 0$\omega =\frac{\pi }{\Delta t}$

(112) The maximum amplitude possible with maximum acceleration a.sub.max=10 m/sec.sup.2 is Distance part with radius Rd:

(113) $A=\frac{a_{\max }}{{\left(\frac{\pi }{\Delta t}\right)}^2}$$s\left(t\right)=A.Math.\left(1-\cos \left(\frac{\pi }{\Delta t}t\right)\right)$

(114) Another function that is used to define such a transition is the sigmoid function as described in WO9716760 and U.S. Pat. No. 6,871,953. The sigmoid function is defined as (FIG. 18):

(115) $y\left(t\right)=\frac{1}{1+e^{-t}}$

(116) If y(t) is the displacement as a function of time t, then the acceleration in the sigmoid profile (FIG. 19) is given by:

(117) $a=\frac{d^{2}y\left(t\right)}{d{t}^2}$$a=\frac{2e^{-2t}}{{\left(e^{-t}+1\right)}^3}-\frac{e^{-t}}{{\left(e^{-t}+1\right)}^2}$

(118) It shows the acceleration in the profile is not uniform. The maximum acceleration possible is not utilised during the whole transition. The speed of the transition is restricted by the extremes in the acceleration profile, see FIG. 19.

(119) The sigmoid function can be scaled and translated to model the required transition. In the same way as shown

(120) with the cosine transition it can be easily shown that a transition that is described by a sigmoid function is less optimal. That is when limited to a maximum acceleration during the transition: The maximum displacement in a fixed time interval is less

(121) The time needed for a required tool displacement is larger resulting in a wider transition zone.
Rd:=10.0
zd(r):=Rd=√{square root over (Rd.sup.2−r.sup.2)} Reading part with radius Rr
Rr:=8.5
zr(r):=Rr−√{square root over (Rr.sup.2−r.sup.2)} Sagitta difference or height difference when moving from reading part to distance part, see FIG. 30:
saggdiff(r):=zr(r)−zd(r)

(122) Radial distance s available to take height step when the transition is performed between two meridians that are a angle α apart at a distance r from the optical centre:

(123) $\left(r\right):=2.Math.\pi .Math.r.Math.\frac{\alpha }{360}$

(124) Transition profile in the first half part
z:=½.Math.a.Math.x.sup.2

(125) Should be equal to half the height step

(126) $\frac{\mathrm{saggdiff}\left(r\right)}{2}=\frac{1}{2}.Math.a.Math.{\left(\frac{s\left(x\right)}{2}\right)}^2$$a:=\frac{\mathrm{saggdiff}\left(r\right)}{{\left(\frac{s\left(x\right)}{2}\right)}^2}$$a:=\frac{4.Math.\mathrm{saggdiff}\left(r\right)}{{s\left(x\right)}^2}$$a:=4.Math.\frac{\left[Rr-\sqrt{R{r}^2-r^2}-\left(\mathrm{Rd}-\sqrt{{\mathrm{Rd}}^2-r^2}\right]\right)}{{\left(2.Math.\pi .Math.r.Math.\frac{\alpha }{360}\right)}^2}$

(127) Slope half way the transition profile:

(128) $\mathrm{slope}:=\left[\frac{d}{dx}{\left(\frac{1}{2}.Math.a.Math.x\right)}^2\right]$$\mathrm{slope}:=a.Math.x$$\mathrm{slope}:=a.Math.\frac{\left(2.Math.\pi .Math.r.Math.\frac{\alpha }{250}\right)}{2}$$:=4.Math.\frac{\left[\mathrm{Rr}-\sqrt{R{r}^2-r^2}-\left(\mathrm{Rd}-\sqrt{R{d}^2-r^2}\right)\right]}{{\left(2.Math.\pi .Math.r.Math.\frac{\alpha }{360}\right)}^2}.Math.\frac{\left(2.Math.\pi .Math.r.Math.\frac{\alpha }{360}\right)}{2}$$:=\frac{\left[\mathrm{Rr}-\sqrt{R{r}^2-r^2}-\left(\mathrm{Rd}-\sqrt{R{d}^2-r^2}\right)\right]}{\left(\pi .Math.r.Math.\frac{\alpha }{360}\right)}$

(129) See FIG. 32, showing a graph of the slope or first derivative of the steepest part of the blending part as a function of the radial distance from the optical centre of the ophthalmic lens, for a blending zone between two semi meridian lines enclosing an angle of 15 degrees, and FIG. 32, for a blending part enclosed by two semi meridians enclosing an angle of 4 degrees. Below, several values are shown in a table

(130) TABLE-US-00008 Distance slope 15 deg slope 4 deg 0.4 0.027 0.101 0.8 0.054 0.203 1.2 0.082 0.307 1.6 0.11 0.414 2.0 0.14 0.524 2.4 0.171 0.64 2.8 0.203 0.761

(131) The shape and slope (first derivative) of the blending zone can be measured with high accuracy, using for instance a 3D Optical Profiler or Form talysurf, commercial available from Taylor Hobson, the United Kingdom. FIG. 35 shows a surface map of a lens according to the invention.

(132) It was found in clinical trials that with a steep slope and careful choice of central part, the contrast of the lens increases. In a recent performed European multicentric clinical study (Pardubice study data on file), 25 subjects with 49 eyes, 24 subjects were bilateral implanted with the inventive MSIOL. These subjects represent a sample selection of the population of typical European cataract patients. The contrast sensitivity was measured under photopic conditions with a CSV1000 instrument from Vector Vision Inc, Greenville, Oh., USA U.S. Pat. No. 5,078,486. In this study the following LogMar (Logarithmic Mean Angle Resolution) values, measured with the CSV1000, where found for spatial frequencies 3, 6, 12 and 18 cpd:

(133) TABLE-US-00009 spatial frequency (cpd) 3 months StDev 3 1.677 +/− 0.15 6 2.073 +/− 0.17 12 1.831 +/− 0.21 18 1.437 +/− 0.19

(134) A contrast sensitivity comparison was made with the two market leaders in MIOL. The AcrySof ReSTOR SN60D3 (Alcon) is a refractive/diffractive MIOL and the ReZoom (Advanced Medical Optics) is a multizone refractive multifocal aiming improved visual outcome.

(135) In a recent study titled “Multifocal Apodized Diffractive IOL versus Multifocal Refractive IOL” published in the Journal Cataract Refract Surg 2008; 34:2036-2042 Q 2008 ASCRS and ESCRS, contrast sensitivity was measured in 23 patients who had bilateral implantation of the AcryS of ReSTOR SN60D3 IOL and 23 patients who had bilateral implantation of the ReZoom IOL. The number of subjects in our study was 24 and therefore direct comparable with the outcome of this study. It shows a mean contrast sensitivity improvement of at least 25% compared with a state of the art concentric refractive multifocal lens. The inventive lens configuration will give a mean contrast sensitivity for healthy eyes (1.677) at 3 cpd, (2.07) at 6 cpd, (1.831) at 12 cpd and (1.437) at 18 cpd. In FIGS. 33 and 34, the results are indicated when compared to the performance of an average population, for several age groups (Pop. Norm http://www.vectorvision.com/html/educationCSV1000Norms.html), the performance of the test group before surgery (pre-op), and the performance with an MIOL indicated as LS 312-MF. These results were found consistent at 6 months post operative, i.e., 6 months after surgery.

(136) It will also be clear that the above description and drawings are included to illustrate some embodiments of the invention, and not to limit the scope of protection. Starting from this disclosure, many more embodiments will be evident to a skilled person which are within the scope of protection and the essence of this invention and which are obvious combinations of prior art techniques and the disclosure of this patent.