CN113599021B - Aspherical intraocular lens for resisting postoperative residual refractive error - Google Patents
Aspherical intraocular lens for resisting postoperative residual refractive error Download PDFInfo
- Publication number
- CN113599021B CN113599021B CN202110624108.8A CN202110624108A CN113599021B CN 113599021 B CN113599021 B CN 113599021B CN 202110624108 A CN202110624108 A CN 202110624108A CN 113599021 B CN113599021 B CN 113599021B
- Authority
- CN
- China
- Prior art keywords
- aspherical
- intraocular lens
- optical
- polynomial
- mtf
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
- Active
Links
- 208000014733 refractive error Diseases 0.000 title claims abstract description 27
- 230000002980 postoperative effect Effects 0.000 title claims abstract description 20
- 230000003287 optical effect Effects 0.000 claims abstract description 90
- 230000004075 alteration Effects 0.000 claims abstract description 38
- 238000000034 method Methods 0.000 claims description 13
- 239000000463 material Substances 0.000 claims description 9
- 230000002035 prolonged effect Effects 0.000 claims description 4
- 238000010276 construction Methods 0.000 claims 1
- 238000002513 implantation Methods 0.000 abstract description 15
- 208000029091 Refraction disease Diseases 0.000 abstract description 8
- 230000004430 ametropia Effects 0.000 abstract description 8
- 230000000007 visual effect Effects 0.000 abstract description 7
- 238000012634 optical imaging Methods 0.000 abstract description 6
- 230000035945 sensitivity Effects 0.000 abstract description 5
- 210000001508 eye Anatomy 0.000 description 43
- 238000005457 optimization Methods 0.000 description 14
- 208000002177 Cataract Diseases 0.000 description 11
- 230000002209 hydrophobic effect Effects 0.000 description 11
- 230000004044 response Effects 0.000 description 9
- 208000008516 Capsule Opacification Diseases 0.000 description 8
- -1 acrylic ester Chemical class 0.000 description 8
- 210000004087 cornea Anatomy 0.000 description 8
- 210000001747 pupil Anatomy 0.000 description 6
- 238000001356 surgical procedure Methods 0.000 description 6
- 239000000758 substrate Substances 0.000 description 5
- 210000005252 bulbus oculi Anatomy 0.000 description 4
- 238000006243 chemical reaction Methods 0.000 description 4
- 238000001514 detection method Methods 0.000 description 4
- 229910003460 diamond Inorganic materials 0.000 description 4
- 239000010432 diamond Substances 0.000 description 4
- 238000005516 engineering process Methods 0.000 description 4
- 238000003754 machining Methods 0.000 description 4
- 238000003801 milling Methods 0.000 description 4
- 238000007517 polishing process Methods 0.000 description 4
- 238000002360 preparation method Methods 0.000 description 4
- 238000003825 pressing Methods 0.000 description 4
- 238000004458 analytical method Methods 0.000 description 3
- 238000010586 diagram Methods 0.000 description 3
- 238000006073 displacement reaction Methods 0.000 description 3
- 229920000058 polyacrylate Polymers 0.000 description 3
- 238000004088 simulation Methods 0.000 description 3
- 230000000694 effects Effects 0.000 description 2
- 230000008569 process Effects 0.000 description 2
- 201000004569 Blindness Diseases 0.000 description 1
- 230000009286 beneficial effect Effects 0.000 description 1
- 230000008901 benefit Effects 0.000 description 1
- 238000004364 calculation method Methods 0.000 description 1
- 230000008859 change Effects 0.000 description 1
- 238000009826 distribution Methods 0.000 description 1
- 238000000605 extraction Methods 0.000 description 1
- 239000007943 implant Substances 0.000 description 1
- 230000006872 improvement Effects 0.000 description 1
- 238000007689 inspection Methods 0.000 description 1
- 230000000750 progressive effect Effects 0.000 description 1
- 230000006641 stabilisation Effects 0.000 description 1
- 238000011105 stabilization Methods 0.000 description 1
- 230000000451 tissue damage Effects 0.000 description 1
- 231100000827 tissue damage Toxicity 0.000 description 1
- 230000007704 transition Effects 0.000 description 1
- 230000037314 wound repair Effects 0.000 description 1
Classifications
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/14—Eye parts, e.g. lenses, corneal implants; Implanting instruments specially adapted therefor; Artificial eyes
- A61F2/16—Intraocular lenses
- A61F2/1613—Intraocular lenses having special lens configurations, e.g. multipart lenses; having particular optical properties, e.g. pseudo-accommodative lenses, lenses having aberration corrections, diffractive lenses, lenses for variably absorbing electromagnetic radiation, lenses having variable focus
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2/00—Filters implantable into blood vessels; Prostheses, i.e. artificial substitutes or replacements for parts of the body; Appliances for connecting them with the body; Devices providing patency to, or preventing collapsing of, tubular structures of the body, e.g. stents
- A61F2/02—Prostheses implantable into the body
- A61F2/14—Eye parts, e.g. lenses, corneal implants; Implanting instruments specially adapted therefor; Artificial eyes
- A61F2/16—Intraocular lenses
- A61F2/1613—Intraocular lenses having special lens configurations, e.g. multipart lenses; having particular optical properties, e.g. pseudo-accommodative lenses, lenses having aberration corrections, diffractive lenses, lenses for variably absorbing electromagnetic radiation, lenses having variable focus
- A61F2/1637—Correcting aberrations caused by inhomogeneities; correcting intrinsic aberrations, e.g. of the cornea, of the surface of the natural lens, aspheric, cylindrical, toric lenses
- A61F2/164—Aspheric lenses
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61F—FILTERS IMPLANTABLE INTO BLOOD VESSELS; PROSTHESES; DEVICES PROVIDING PATENCY TO, OR PREVENTING COLLAPSING OF, TUBULAR STRUCTURES OF THE BODY, e.g. STENTS; ORTHOPAEDIC, NURSING OR CONTRACEPTIVE DEVICES; FOMENTATION; TREATMENT OR PROTECTION OF EYES OR EARS; BANDAGES, DRESSINGS OR ABSORBENT PADS; FIRST-AID KITS
- A61F2240/00—Manufacturing or designing of prostheses classified in groups A61F2/00 - A61F2/26 or A61F2/82 or A61F9/00 or A61F11/00 or subgroups thereof
- A61F2240/001—Designing or manufacturing processes
Landscapes
- Health & Medical Sciences (AREA)
- Ophthalmology & Optometry (AREA)
- Cardiology (AREA)
- Oral & Maxillofacial Surgery (AREA)
- Transplantation (AREA)
- Engineering & Computer Science (AREA)
- Biomedical Technology (AREA)
- Heart & Thoracic Surgery (AREA)
- Vascular Medicine (AREA)
- Life Sciences & Earth Sciences (AREA)
- Animal Behavior & Ethology (AREA)
- General Health & Medical Sciences (AREA)
- Public Health (AREA)
- Veterinary Medicine (AREA)
- Prostheses (AREA)
Abstract
The invention discloses an aspherical intraocular lens for resisting postoperative residual ametropia, which comprises an optical main body (1), a first supporting tab (2) and a second supporting tab (3), wherein the optical main body (1) adopts an aspherical design represented by a Q-type polynomial, an optical zone has a focal depth extending function, optical imaging excess resolution is reasonably utilized, and operation fault tolerance is improved; the lens is better adapted to slight intraocular lens deviation, the sensitivity of focal power and image quality to implantation positions is reduced, residual refractive errors after operation are resisted, and visual satisfaction is improved; meanwhile, high-order aberration is considered, and higher resolution is kept.
Description
Technical Field
The invention relates to the technical field of intraocular lenses, in particular to an aspherical intraocular lens designed by a Q-type polynomial equation and used for resisting postoperative residual refractive errors.
Background
Intraocular lenses and corresponding surgical techniques have been rapidly developed over decades, and the lens replacement surgery has been developed from the initial transition from large-incision extracapsular extraction to the current small-incision phacoemulsification combined intraocular lens implantation, with short surgical time, small tissue damage, and rapid wound repair. Cataract treatment has also evolved from traditional blind surgery to more challenging refractive surgery, where the patient's eye is not only visible, but also clear and good looking.
It is well known that the cornea of a person is orthoglobally affected. Under a large pupil, the marginal rays are refracted to a much greater extent than the central ray, and the focal point is not perfectly focused. Standard spherical intraocular lenses are also positive spherical, with the implant eye differences increasing further. The aspherical surface can compensate the positive spherical aberration of the human eye by changing the shape of the edge of the lens to avoid the increase of the positive spherical aberration of the whole eye implanted into the eye, and especially the aspherical surface with the negative spherical aberration design can make the whole eyeball difference return to zero. A series of aspherical intraocular lenses, 0 spherical aberration, -0.27um, -0.2um, are found in the market, and the design concept is also endless, high order aspherical, non-constant (EP 2034928B 1), axial progressive (CN 201811301451), etc.
However, in real world applications, the effect of aspheric spherical aberration adjustment is typically very small compared to equivalent spherical power, with a significant portion of the post-operative residual refractive errors being more than 50 degrees (the main cause of the blindness). The clinical ophthalmology professor Jay s.pepose, medical director at the medical doctor, pepose vision institute, the university of washington, and the barn jejunos hospital, believes that only in the presence of a significant improvement in vision quality, the manufacturer has reason to pay more for the non-curved surfaces for the patient, but most patients do not notice the differences in these non-curved surfaces. Only in low contrast conditions, such as driving in dusk, is it possible for a patient with a large pupil to notice the discrepancy, whereas the pupil of a normal cataract patient is not very large. And the pupils of the human eyes tend to be gradually contracted with the age.
Parker also believes that any optical design of spherical aberration adjustment may be insignificant compared to the spherical aberration changes caused by the procedure itself. One study found that small incision cataract surgery induced spherical aberration averaged 0.03±0.17um, with 86.7% of the surgical-eye-derived spherical aberration varied by around 0.1 μm in his study. The difference of most manufacturer's spherical aberration optimization is about 0.1um, and the spherical aberration distribution of the whole eyes after operation can be out of control due to the change of the spherical aberration of operation source.
For some aspherical intraocular lenses, position dependence is another, more important issue. Standard spherical intraocular lenses, while increasing the positive spherical aberration of the optical system, do not create significant problems if they are off-centered. However, aspheric accommodating higher order aberrations designed as negative aberrations are based on ideal positional designs (no tilt, decentration and axial displacement). Devgan doctor considers that the ideal center position of the intraocular lens is impractical in a complex intraocular environment. Tilting, decentering and axial displacement often occur, and axial displacement is also an important cause of full-eye equivalent sphere power variation. In this case, the spherical aberration modulation hardly exerts its function.
In summary, the patient's eye is difficult to perceive spherical aberration, limited by pupil size, contrast in the environment, intraoperative spherical aberration, intraocular lens misalignment, and the like. The patient's eye really requires not spherical aberration adjustment, but rather precision and stabilization of the postoperative diopter, i.e. less postoperative residual refractive error.
Disclosure of Invention
In response to the foregoing problems with the prior art, the applicant provides a design of an aspherical intraocular lens that resists post-operative residual refractive errors. The optical main body has a Q-type polynomial aspheric surface design, the excessive resolution of optical imaging is reasonably utilized, the focal depth is prolonged, and the operation fault tolerance is improved; the lens is better adapted to slight intraocular lens deviation, the sensitivity of focal power and image quality to implantation positions is reduced, residual refractive errors after operation are resisted, and visual satisfaction is improved; meanwhile, high-order aberration is considered, and higher resolution is kept.
The technical scheme of the invention is as follows:
an aspherical intraocular lens for resisting postoperative residual ametropia, the intraocular lens comprises an optical main body (1), a first supporting tab (2) and a second supporting tab (3), wherein the optical main body (1) adopts an aspherical design of Q-type polynomial representation, and the range of a defocus curve is widened on the premise of ensuring a certain total area to resist the postoperative residual ametropia.
The optical main body (1), the first supporting loop (2) and the second supporting loop (3) are of an integrated structure, and are integrally formed by adopting the same material.
The periphery of the optical main body (1) is provided with a square edge with a right angle of 360 degrees, so that the generation of the secondary cataract is effectively inhibited.
The optical body (1) consists of two optical surfaces, either spherical or aspherical, wherein at least one surface is of aspherical design characterized by a polynomial of the type Q, in particular a strong aspherical surface Q con "or" mild asphereQ bfs ", for Q bfs An aspherical surface, the expression of which is:
h is the vertical distance from any point on the aspheric surface to the optical axis Z, h 2 ＝x 2 +y 2 ,ρ bfs Is Q bfs The curvature of the aspherical best-fit sphere, r is the normalized half aperture, and K is the conic coefficient of the reference quadric. a, a m For each coefficient of the additional polynomial, m=0, 1, 2, 3 … M, M being the highest degree of the additional polynomial.Is a group of a m The m-order orthogonalization Jacobi polynomial for the coefficient is:
q-type aspheric surface phase contrastThe advantage of the aspherical surface of the even polynomial is that on one hand, the orthogonal substrate is adopted by the additional polynomial, and the contributions of the coefficients of the additional polynomial to the aspherical surface type cannot be mutually counteracted, so that the optimization efficiency is improved. On the other hand, cosine factor is introducedIt will Q bfs The deviation of the aspheric surface from the best-fit spherical surface is converted from being along the optical axis to being along the normal direction, Q bfs Root mean square slope K of aspheric surface deviating along normal RMS Proportional to the sum of coefficients of the additional polynomials and proportional to the density of directly testable surface interference fringes. The designer can control K RMS And the non-spherical surface processing yield is improved.
The magnitude of each coefficient of the Q-type polynomial aspheric surface is directly related to the gradient or the sagittal deviation of the aspheric surface relative to the basal spherical surface or the conical surface, so that the aspheric surface parameters can be optimized and adjusted in the processing process. In particular, the problems of manufacturability and testability of the aspherical surface are solved, and the coefficient can determine the sagittal height and the gradient deviation of the basal plane through appearance inspection.
The diameter of the effective optical area of the optical main body (1) is 5.5-6.5 mm, and the thickness of the center is 0.45-1.55 mm; the thickness of the first supporting loop (2) and the second supporting loop (3) is 0.15-0.45 mm.
The optical body (1) and the conventional aspherical intraocular lens are 50mm thick -1 The lower MTF defocus curves of (a) have the same surrounding area.
The focal depth of the optical main body (1) is prolonged by more than 0.5D compared with that of a conventional aspheric intraocular lens, and the comfort level of the surgical eye is improved under the condition of precise surgery. And the comfort level of the operation eyes is improved under the condition of accurate operation. In the eye model, 50lp/mm defocus curve under 3mm diaphragm uses MTF@50 lp/mm=0.2 as a reference line of focal depth, and the focal depth range DF and MTF peak MTF max The method meets the following conditions:
a is the normalized area enclosed by the defocus curve and the horizontal axis, and the defocus position 1D and MTF0.1 are normalized length units.
The intraocular lens, MTF@50mm in a simulated eye -1 ＞0.6、MTF@100mm -1 > 0.43 or > 0.28.
The spherical aberration of the optical main body (1) is-0.1 um to-0.27 um;
the optical main body (1) improves the operation fault tolerance, and counteracts the power calibration error, the preoperative power calculation error, the equivalent sphere power residual error caused by the front-back deviation of the postoperative intraocular lens and the like in the process of producing the intraocular lens to a certain extent.
The invention also provides a preparation method of the aspherical intraocular lens for resisting postoperative residual ametropia, which comprises the following steps:
(1) First, determining a design target: optical power, spherical aberration, extended focal depth, etc.
(2) The basic equation for a conventional aspherical surface is determined by designing the spherical aberration value. The incident wavelength is 546nm monochromatic, an initial model is built in Zemax, and an L-B eye model is generally selected:
the target value of the standard spherical error item Z (4, 0) is indirectly obtained by optimizing the ZERN 9 in the Zernike Fringe polynomial, and the conventional aspheric expression is determined:
h is the vertical distance from any point on the aspheric surface to the optical axis Z, h 2 ＝x 2 +y 2 ,ρ bfs Is Q bfs The curvature of the aspherical best-fit sphere, r is the normalized half aperture.
(3) And obtaining a defocus curve according to a conventional aspheric base structure, calculating a normalized area surrounded by the defocus curve and a transverse axis, and taking defocus position 1D and MTF0.1 as normalized length units.
(4) According to the target focal depth extension range, combining DF-MTFmax conversion formula to reversely deduce MTFmax
In the eye model, 50lp/mm defocus curves under a 3mm diaphragm take MTF@50 lp/mm=0.2 as a reference line of focal depth, and the focal depth range DF and the MTF peak value MTFmax satisfy the following conditions:
(5) The extension term is added to the suffix of the conventional aspheric expression, the term is 3-4 terms, m=0, 1, 2 and 3 are taken as examples, and 3 is the highest degree of the additional polynomial.The method comprises the following steps:
the initial value of the Q-type polynomial aspheric expression is formed:
(6) Returning to Zemax, MFT@50lp/mm is optimized, the target value being MTFmax in step (4). Obtaining each item in the step (5) through cone optimization, global optimization and the likeCoefficients.
(7) And determining the final surface profile according to the optimized Q-type polynomial non-curved equation.
(8) Lathe, milling machine, polishing process. The hydrophobic acrylic ester sheet base for processing is obtained by adopting a mould pressing mode, and has a biconvex structure, wherein the periphery of the rear surface (the optical surface close to the capsular bag after implantation) is provided with a square edge with a right angle of 360 degrees, so that the generation of the secondary cataract is effectively inhibited. For hydrophobic acrylic ester, the material reaches a glassy state at low temperature, and a Q-type polynomial aspheric surface is machined on the front surface (optical surface close to cornea after implantation) of the substrate by adopting an optical cold machining method and a diamond single-point turning technology.
(9) Optical detection, MTF versus defocus position response curve and MTF versus spatial frequency response curve were measured in ISO simulated eye/Model eye 2. Judging whether the focal depth extension range reaches a target value or not, and simultaneously checking whether the MTF under hundred-millimeter line pairs meets the requirements of YY0290.2 or not: greater than 0.43, or in any case not less than 0.28.
(10) And (3) judging that if the map in the step (9) does not meet the design requirement, returning to the step (6) for re-optimization until the requirement in the step (9) is met, and finishing the design.
The beneficial technical effects of the invention are as follows:
the optical area of the optical main body (1) adopts a Q-type polynomial aspheric surface, so that the excessive resolution of optical imaging is reasonably utilized, the focal depth is prolonged, and the operation fault tolerance is improved;
the optical area of the optical main body (1) is better suitable for slight intraocular lens deflection, reduces the sensitivity of focal power and image quality to implantation positions, resists residual refractive errors after operation, and improves visual satisfaction;
the optical zone of the optical body (1) gives consideration to higher-order aberration and keeps higher resolution.
The optical area of the optical main body (1) always keeps a certain focal depth under different pupils, and the visual quality is good.
Drawings
FIG. 1 is a schematic diagram of the structure of an embodiment 1 of the present invention;
FIG. 2 is a schematic structural diagram of embodiment 2 of the present invention;
FIG. 3 is a schematic structural diagram of embodiment 3 of the present invention;
FIG. 4 is a graph showing MTF@50lp/mm versus power for a conventional aspherical intraocular lens under a simulated eye;
FIG. 5 is a plot of MTF@50lp/mm versus optical power for example 1 of the present invention under simulated eye;
FIG. 6 is a plot of MTF@50lp/mm versus optical power for example 2 of the present invention under simulated eye;
FIG. 7 is a plot of MTF@50lp/mm versus optical power for example 3 of the present invention under simulated eye;
FIG. 8 is a graph of MTF versus spatial frequency for a conventional aspherical intraocular lens under a simulated eye;
FIG. 9 is a plot of MTF versus spatial frequency for example 1 under simulated eye conditions;
FIG. 10 is a plot of MTF versus spatial frequency for example 2 under simulated eye conditions;
FIG. 11 is a plot of MTF versus spatial frequency for example 3 under simulated eye conditions;
Detailed Description
The present invention will be described in detail below with reference to the drawings and examples.
Example 1
As shown in fig. 1, the intraocular lens comprises an optical main body (1), a first supporting tab (2) and a second supporting tab (3), wherein the optical main body (1) adopts an aspherical design characterized by a Q-type polynomial, and the range of a defocus curve is widened on the premise of ensuring a certain total area to resist the residual refractive error after operation.
The optical main body (1), the first supporting loop (2) and the second supporting loop (3) are of an integrated structure, and are integrally formed by adopting the same material.
The periphery of the optical main body (1) is provided with a square edge with a right angle of 360 degrees, so that the generation of the secondary cataract is effectively inhibited.
The optical body (1) consists of two optical surfaces, either spherical or aspherical, wherein at least one surface is of aspherical design characterized by a polynomial of the type Q, in particular a strong aspherical surface Q con "or" mild aspheric surface Q bfs ”。
A lenticular lens sheet having an effective optical area of the optical body (1) with a diameter of 6.0mm and a center thickness of 0.80 mm; the thickness of the first supporting loop (2) and the second supporting loop (3) is 0.35mm;
the optical body 1 is made of a hydrophobic polyacrylate having a refractive index of 1.45 to 1.55 and an Abbe's number of 45 to 55.
The preparation method of the intraocular lens comprises the following steps:
(1) First, determining a design target: optical power=20d, spherical aberration= -0.1um, focal depth extension range not less than 0.5D, etc.
(2) The basic equation for a conventional aspherical surface is determined by designing the spherical aberration value. The incident wavelength is 546nm monochromatic, an initial model is built in Zemax, and an L-B eye model is generally selected:
the target value of the standard spherical error item Z (4, 0) is indirectly obtained by optimizing the ZERN 9 in the Zernike Fringe polynomial, and the conventional aspheric expression is determined:
h is the vertical distance from any point on the aspheric surface to the optical axis Z, h 2 ＝x 2 +y 2 ,ρ bfs Is Q bfs The curvature of the aspherical best-fit sphere, r is the normalized half aperture.
Total eyeball difference Z (4, 0) =0.14 um, combined with the L-B eye model cornea spherical aberration being +0.24um, the back-push results in intraocular lens aspheric spherical aberration being-0.1 um. Meets the design requirement.
(3) From the conventional aspherical base structure, a defocus curve is obtained, and a normalized area surrounded by the defocus curve and the horizontal axis is calculated, taking defocus position 1D and MTF0.1 as normalized length units, as in fig. 4, a= 6.808.
(4) According to the target focal depth extension range, combining DF-MTFmax conversion formula to reversely deduce MTFmax
In the eye model, 50lp/mm defocus curves under a 3mm diaphragm take MTF@50 lp/mm=0.2 as a reference line of focal depth, and the focal depth range DF and the MTF peak value MTFmax satisfy the following conditions:
(5) The extension term is added to the suffix of the conventional aspheric expression, the term is 3-4 terms, m=0, 1, 2 and 3 are taken as examples, and 3 is the highest degree of the additional polynomial.The method comprises the following steps:
the initial value of the Q-type polynomial aspheric expression is formed:
(6) Returning to Zemax, MFT@50lp/mm is optimized, the target value being MTFmax in step (4). Obtaining each item in the step (5) through cone optimization, global optimization and the likeCoefficients.
(7) And determining the final surface profile according to the optimized Q-type polynomial non-curved equation.
(8) Lathe, milling machine, polishing process. The hydrophobic acrylic ester sheet base for processing is obtained by adopting a mould pressing mode, and has a biconvex structure, wherein the periphery of the rear surface (the optical surface close to the capsular bag after implantation) is provided with a square edge with a right angle of 360 degrees, so that the generation of the secondary cataract is effectively inhibited. For hydrophobic acrylic ester, the material reaches a glassy state at low temperature, and a Q-type polynomial aspheric surface is machined on the front surface (optical surface close to cornea after implantation) of the substrate by adopting an optical cold machining method and a diamond single-point turning technology.
(9) Optical detection, MTF versus defocus position response curve and MTF versus spatial frequency response curve were measured in ISO simulated eye/Model eye 2. Judging whether the focal depth extension range reaches a target value or not, and simultaneously checking whether the MTF under hundred-millimeter line pairs meets the requirements of YY0290.2 or not: greater than 0.43, or in any case not less than 0.28.
(10) And (3) judging that if the map in the step (9) does not meet the design requirement, returning to the step (6) for re-optimization until the requirement in the step (9) is met, and finishing the design.
Analysis and discussion of results:
the aspheric intraocular lens for resisting residual ametropia after operation reasonably utilizes the excessive resolution of optical imaging and prolongs the focal depth. As can be seen from fig. 5, the depth of focus range df=1.68d, which is extended by 0.56D from the conventional aspherical (df=1.12D) depth of focus, is a reference line of the depth of focus of mtf@50 lp/mm=0.2. This indicates that this embodiment increases surgical fault tolerance; better adapts to slight artificial lens deflection, reduces focal power and image qualitySensitivity to implantation position, and can be used for resisting postoperative residual ametropia and improving visual satisfaction. Calculate the defocus curve area in FIG. 5 to give A Example 1 = 6.808, consistent with conventional aspheres, indicating that the light energy utilization is the same as conventional aspheres.
Meanwhile, as can be seen from fig. 9, under the simulation eyes, the mtf@100lp/mm=0.5 meets the requirement of the conventional YY0290.2 on the conventional monofocal image quality. This shows that this embodiment meets the requirements of a conventional aspherical monofocal point, maintaining a higher resolution.
To sum up, embodiment 1 meets the design requirements.
Example 2
As shown in fig. 2, an aspherical intraocular lens for combating post-operative residual refractive error, the intraocular lens comprising an optical body (1), a first haptic (2) and a second haptic (3), the optical body (1) combating post-operative residual refractive error.
The optical main body (1), the first supporting loop (2) and the second supporting loop (3) are of an integrated structure, and are integrally formed by adopting the same material.
The periphery of the optical main body (1) is provided with a square edge with a right angle of 360 degrees, so that the generation of the secondary cataract is effectively inhibited.
The optical body (1) consists of two optical surfaces, either spherical or aspherical, wherein at least one surface is of aspherical design characterized by a polynomial of the type Q, in particular a strong aspherical surface Q con "or" mild aspheric surface Q bfs ”。
A lenticular lens sheet having an effective optical area of the optical body (1) with a diameter of 6.0mm and a center thickness of 0.80 mm; the thickness of the first supporting loop (2) and the second supporting loop (3) is 0.35mm;
the optical body 1 is made of a hydrophobic polyacrylate having a refractive index of 1.45 to 1.55 and an Abbe's number of 45 to 55.
The preparation method of the intraocular lens comprises the following steps:
(1) First, determining a design target: optical power=20d, spherical aberration= -0.15um, focal depth extension range not less than 0.8D, etc.
(2) The basic equation for a conventional aspherical surface is determined by designing the spherical aberration value. The incident wavelength is 546nm monochromatic, an initial model is built in Zemax, and an L-B eye model is generally selected:
the target value of the standard spherical error item Z (4, 0) is indirectly obtained by optimizing the ZERN 9 in the Zernike Fringe polynomial, and the conventional aspheric expression is determined:
h is the vertical distance from any point on the aspheric surface to the optical axis Z, h 2 ＝x 2 +y 2 ,ρ bfs Is Q bfs The curvature of the aspherical best-fit sphere, r is the normalized half aperture.
Total eyeball difference Z (4, 0) =0.09 um, combined with the L-B eye model cornea spherical aberration is +0.24um, and the back-push results in intraocular lens aspheric spherical aberration of-0.15 um. Meets the design requirement.
(3) From the conventional aspherical base structure, a defocus curve is obtained, and a normalized area surrounded by the defocus curve and the horizontal axis is calculated, taking defocus position 1D and MTF0.1 as normalized length units, as in fig. 4, a= 6.808.
(4) According to the target focal depth extension range, combining DF-MTFmax conversion formula to reversely deduce MTFmax
In the eye model, 50lp/mm defocus curves under a 3mm diaphragm take MTF@50 lp/mm=0.2 as a reference line of focal depth, and the focal depth range DF and the MTF peak value MTFmax satisfy the following conditions:
(5) The extension term is added to the suffix of the conventional aspheric expression, the term is 3-4 terms, m=0, 1, 2 and 3 are taken as examples, and 3 is the highest degree of the additional polynomial.The method comprises the following steps:
the initial value of the Q-type polynomial aspheric expression is formed:
(6) Returning to Zemax, MFT@50lp/mm is optimized, the target value being MTFmax in step (4). Obtaining each item in the step (5) through cone optimization, global optimization and the likeCoefficients.
(7) And determining the final surface profile according to the optimized Q-type polynomial non-curved equation.
(8) Lathe, milling machine, polishing process. The hydrophobic acrylic ester sheet base for processing is obtained by adopting a mould pressing mode, and has a biconvex structure, wherein the periphery of the rear surface (the optical surface close to the capsular bag after implantation) is provided with a square edge with a right angle of 360 degrees, so that the generation of the secondary cataract is effectively inhibited. For hydrophobic acrylic ester, the material reaches a glassy state at low temperature, and a Q-type polynomial aspheric surface is machined on the front surface (optical surface close to cornea after implantation) of the substrate by adopting an optical cold machining method and a diamond single-point turning technology.
(9) Optical detection, MTF versus defocus position response curve and MTF versus spatial frequency response curve were measured in ISO simulated eye/Model eye 2. Judging whether the focal depth extension range reaches a target value or not, and simultaneously checking whether the MTF under hundred-millimeter line pairs meets the requirements of YY0290.2 or not: greater than 0.43, or in any case not less than 0.28.
(10) And (3) judging that if the map in the step (9) does not meet the design requirement, returning to the step (6) for re-optimization until the requirement in the step (9) is met, and finishing the design.
Analysis and discussion of results:
the aspheric intraocular lens for resisting residual ametropia after operation reasonably utilizes the excessive resolution of optical imaging and prolongs the focal depth. As can be seen from fig. 6, the depth of focus range df=1.95D is extended by 0.83D from the conventional aspherical (df=1.12d) depth of focus with mtf@50 lp/mm=0.2 as the reference line of depth of focus. This indicates that this embodiment increases surgical fault tolerance; the lens is better suitable for slight intraocular lens deflection, reduces the sensitivity of focal power and image quality to implantation positions, resists residual refractive errors after operation, and improves visual satisfaction. Calculate the defocus curve area in FIG. 6 to give A Example 2 = 6.808, consistent with conventional aspheres, indicating that the light energy utilization is the same as conventional aspheres.
Meanwhile, as can be seen from fig. 10, under the simulation eyes, the mtf@100lp/mm=0.44 meets the requirement of the conventional YY0290.2 on the conventional monofocal image quality. This shows that this embodiment meets the requirements of a conventional aspherical monofocal point, maintaining a higher resolution.
To sum up, example 2 meets the design requirements.
Example 3
As shown in fig. 3, an aspherical intraocular lens for combating post-operative residual refractive error, the intraocular lens comprising an optical body (1), a first haptic (2) and a second haptic (3), the optical body (1) combating post-operative residual refractive error.
The optical main body (1), the first supporting loop (2) and the second supporting loop (3) are of an integrated structure, and are integrally formed by adopting the same material.
The periphery of the optical main body (1) is provided with a square edge with a right angle of 360 degrees, so that the generation of the secondary cataract is effectively inhibited.
The optical body (1) consists of two optical surfaces, which can beIs spherical or aspherical, wherein at least one surface adopts an aspherical design characterized by a Q-type polynomial, and can be specifically a' strong aspherical Q con "or" mild aspheric surface Q bfs ”。
A lenticular lens sheet having an effective optical area of the optical body (1) with a diameter of 6.0mm and a center thickness of 0.80 mm; the thickness of the first supporting loop (2) and the second supporting loop (3) is 0.35mm;
the optical body 1 is made of a hydrophobic polyacrylate having a refractive index of 1.45 to 1.55 and an Abbe's number of 45 to 55.
The preparation method of the intraocular lens comprises the following steps:
(1) First, determining a design target: optical power=20d, spherical aberration= -0.2um, focal depth extension range not less than 1.0D, etc.
(2) The basic equation for a conventional aspherical surface is determined by designing the spherical aberration value. The incident wavelength is 546nm monochromatic, an initial model is built in Zemax, and an L-B eye model is generally selected:
the target value of the standard spherical error item Z (4, 0) is indirectly obtained by optimizing the ZERN 9 in the Zernike Fringe polynomial, and the conventional aspheric expression is determined:
h is the vertical distance from any point on the aspheric surface to the optical axis Z, h 2 ＝x 2 +y 2 ,ρ bfs Is Q bfs The curvature of the aspherical best-fit sphere, r is the normalized half aperture.
Total eyeball difference Z (4, 0) =0.04 um, combined with the L-B eye model cornea spherical aberration being +0.24um, the back-push results in intraocular lens aspheric spherical aberration being-0.2 um. Meets the design requirement.
(3) From the conventional aspherical base structure, a defocus curve is obtained, and a normalized area surrounded by the defocus curve and the horizontal axis is calculated, taking defocus position 1D and MTF0.1 as normalized length units, as in fig. 4, a= 6.808.
(4) According to the target focal depth extension range, combining DF-MTFmax conversion formula to reversely deduce MTFmax
In the eye model, 50lp/mm defocus curves under a 3mm diaphragm take MTF@50 lp/mm=0.2 as a reference line of focal depth, and the focal depth range DF and the MTF peak value MTFmax satisfy the following conditions:
(5) The extension term is added to the suffix of the conventional aspheric expression, the term is 3-4 terms, m=0, 1, 2 and 3 are taken as examples, and 3 is the highest degree of the additional polynomial.The method comprises the following steps:
the initial value of the Q-type polynomial aspheric expression is formed:
(6) Returning to Zemax, MFT@50lp/mm is optimized, the target value being MTFmax in step (4). Obtaining each item in the step (5) through cone optimization, global optimization and the likeCoefficients.
(7) And determining the final surface profile according to the optimized Q-type polynomial non-curved equation.
(8) Lathe, milling machine, polishing process. The hydrophobic acrylic ester sheet base for processing is obtained by adopting a mould pressing mode, and has a biconvex structure, wherein the periphery of the rear surface (the optical surface close to the capsular bag after implantation) is provided with a square edge with a right angle of 360 degrees, so that the generation of the secondary cataract is effectively inhibited. For hydrophobic acrylic ester, the material reaches a glassy state at low temperature, and a Q-type polynomial aspheric surface is machined on the front surface (optical surface close to cornea after implantation) of the substrate by adopting an optical cold machining method and a diamond single-point turning technology.
(9) Optical detection, MTF versus defocus position response curve and MTF versus spatial frequency response curve were measured in ISO simulated eye/Model eye 2. Judging whether the focal depth extension range reaches a target value or not, and simultaneously checking whether the MTF under hundred-millimeter line pairs meets the requirements of YY0290.2 or not: greater than 0.43, or in any case not less than 0.28.
(10) And (3) judging that if the map in the step (9) does not meet the design requirement, returning to the step (6) for re-optimization until the requirement in the step (9) is met, and finishing the design.
Analysis and discussion of results:
the aspheric intraocular lens for resisting residual ametropia after operation reasonably utilizes the excessive resolution of optical imaging and prolongs the focal depth. As can be seen from fig. 7, the depth of focus range df=2.23D is extended by 1.11D from the conventional aspherical (df=1.12d) depth of focus with mtf@50 lp/mm=0.2 as a reference line of depth of focus. This indicates that this embodiment increases surgical fault tolerance; the lens is better suitable for slight intraocular lens deflection, reduces the sensitivity of focal power and image quality to implantation positions, resists residual refractive errors after operation, and improves visual satisfaction. Calculate the defocus curve area in FIG. 7 to give A Example 3 = 6.808, consistent with conventional aspheres, indicating that the light energy utilization is the same as conventional aspheres.
Meanwhile, as can be seen from fig. 11, under the simulation eyes, the mtf@100lp/mm=0.3 meets the requirement of the conventional YY0290.2 on the conventional monofocal image quality. This shows that this embodiment meets the requirements of a conventional aspherical monofocal point, maintaining a higher resolution.
To sum up, embodiment 3 meets the design requirements.
Claims (3)
1. An aspherical intraocular lens for combating post-operative residual refractive errors, the intraocular lens comprising an optical body (1), a first haptic (2) and a second haptic (3), characterized in that the optical body (1) has a spherical aberration of-0.1 um to-0.27 um, the optical body (1) consists of two optical surfaces, one of which adopts an aspherical design characterized by a polynomial of type Q, the polynomial of type Q being a gentle aspherical Q bfs The other surface is a sphere; one surface of the conventional aspherical intraocular lens adopts a conventional aspherical surface, and the other surface is a spherical surface;
the intraocular lens and the conventional aspherical intraocular lens are 50mm in length -1 The lower MTF defocus curves have the same surrounding area;
in the L-B eye model, under a 3mm diaphragm, a 50lp/mm defocus curve is prolonged by more than 0.5D compared with the focal depth of a conventional aspherical intraocular lens under the condition of taking MTF@50 lp/mm=0.2 as a datum line of focal depth; depth of focus range DF and MTF peak MTF max The method meets the following conditions:
；
a is the normalized area surrounded by the defocusing curve and the transverse axis, and the defocusing position 1D and the MTF0.1 are taken as normalized length units;
conventional aspherical intraocular lens expression:
；
h is the vertical distance from any point on the aspherical surface to the optical axis Z,is Q bfs Curvature of the aspheric best fit sphere;
mild aspheric surface Q bfs The aspherical intraocular lens expression is:
；
h is the vertical distance from any point on the aspherical surface to the optical axis Z,is Q bfs Curvature of aspheric best fit sphere, r is normalized half aperture, a m For each coefficient of the additional polynomial, m=0, 1, 2, 3 … M, M being the highest degree of the additional polynomial,is a group +.>The m-order orthogonalization Jacobi polynomial for the coefficient is:
，
，
，
，
，
。
2. aspherical intraocular lens for combating post-operative residual refractive errors according to claim 1, characterized in that said optical body (1), first haptics (2) and second haptics (3) are of unitary construction, integrally formed with the same material.
3. Aspherical intraocular lens for combating post-operative residual refractive errors according to claim 1, characterized in that said optical body (1) has a perimeter with a square edge of 360 ° right angle.
Priority Applications (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202110624108.8A CN113599021B (en) | 2021-06-04 | 2021-06-04 | Aspherical intraocular lens for resisting postoperative residual refractive error |
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| CN202110624108.8A CN113599021B (en) | 2021-06-04 | 2021-06-04 | Aspherical intraocular lens for resisting postoperative residual refractive error |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| CN113599021A CN113599021A (en) | 2021-11-05 |
| CN113599021B true CN113599021B (en) | 2024-04-16 |
Family
ID=78303426
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CN202110624108.8A Active CN113599021B (en) | 2021-06-04 | 2021-06-04 | Aspherical intraocular lens for resisting postoperative residual refractive error |
Country Status (1)
| Country | Link |
|---|---|
| CN (1) | CN113599021B (en) |
Citations (11)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US4710193A (en) * | 1986-08-18 | 1987-12-01 | David Volk | Accommodating intraocular lens and lens series and method of lens selection |
| CN101437468A (en) * | 2006-05-05 | 2009-05-20 | 卡尔蔡司医疗技术股份公司 | Aspheric intraocular lens and method for designing such iol |
| CN203208162U (en) * | 2013-04-22 | 2013-09-25 | 爱博诺德（北京）医疗科技有限公司 | Aspherical intraocular lens |
| CN106901873A (en) * | 2017-03-09 | 2017-06-30 | 首都医科大学附属北京同仁医院 | The preparation method of intraocular lens |
| CN107212949A (en) * | 2017-07-12 | 2017-09-29 | 无锡蕾明视康科技有限公司 | A kind of multifocal intraocular lenses |
| CN108814770A (en) * | 2018-04-24 | 2018-11-16 | 南开大学 | A kind of dual area aspherical diffractive type artificial lens with extended depth-of-field performance |
| CN108836571A (en) * | 2018-07-13 | 2018-11-20 | 爱博诺德（北京）医疗科技有限公司 | Artificial lenses |
| CN108938144A (en) * | 2018-06-07 | 2018-12-07 | 无锡蕾明视康科技有限公司 | A kind of diffractive multifocal intraocular lens of smooth position phase |
| CN109363802A (en) * | 2018-11-02 | 2019-02-22 | 无锡蕾明视康科技有限公司 | A kind of progressive modulation type aspheric intraocular lens of axial spherical aberration |
| CN110613532A (en) * | 2019-10-24 | 2019-12-27 | 西安浦勒生物科技有限公司 | Posterior chamber type lens designed by toric surface |
| CN111658232A (en) * | 2020-06-24 | 2020-09-15 | 西安眼得乐医疗科技有限公司 | Clinical decentration and tilt resistant intraocular lens |
Family Cites Families (4)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US20060116763A1 (en) * | 2004-12-01 | 2006-06-01 | Simpson Michael J | Contrast-enhancing aspheric intraocular lens |
| US8740978B2 (en) * | 2007-08-27 | 2014-06-03 | Amo Regional Holdings | Intraocular lens having extended depth of focus |
| AU2009327455C1 (en) * | 2008-12-18 | 2014-04-24 | Alcon Inc. | Intraocular lens with extended depth of focus |
| WO2020079642A1 (en) * | 2018-10-18 | 2020-04-23 | Alcon Inc. | Extended depth of focus intraocular lens |
-
2021
- 2021-06-04 CN CN202110624108.8A patent/CN113599021B/en active Active
Patent Citations (11)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US4710193A (en) * | 1986-08-18 | 1987-12-01 | David Volk | Accommodating intraocular lens and lens series and method of lens selection |
| CN101437468A (en) * | 2006-05-05 | 2009-05-20 | 卡尔蔡司医疗技术股份公司 | Aspheric intraocular lens and method for designing such iol |
| CN203208162U (en) * | 2013-04-22 | 2013-09-25 | 爱博诺德（北京）医疗科技有限公司 | Aspherical intraocular lens |
| CN106901873A (en) * | 2017-03-09 | 2017-06-30 | 首都医科大学附属北京同仁医院 | The preparation method of intraocular lens |
| CN107212949A (en) * | 2017-07-12 | 2017-09-29 | 无锡蕾明视康科技有限公司 | A kind of multifocal intraocular lenses |
| CN108814770A (en) * | 2018-04-24 | 2018-11-16 | 南开大学 | A kind of dual area aspherical diffractive type artificial lens with extended depth-of-field performance |
| CN108938144A (en) * | 2018-06-07 | 2018-12-07 | 无锡蕾明视康科技有限公司 | A kind of diffractive multifocal intraocular lens of smooth position phase |
| CN108836571A (en) * | 2018-07-13 | 2018-11-20 | 爱博诺德（北京）医疗科技有限公司 | Artificial lenses |
| CN109363802A (en) * | 2018-11-02 | 2019-02-22 | 无锡蕾明视康科技有限公司 | A kind of progressive modulation type aspheric intraocular lens of axial spherical aberration |
| CN110613532A (en) * | 2019-10-24 | 2019-12-27 | 西安浦勒生物科技有限公司 | Posterior chamber type lens designed by toric surface |
| CN111658232A (en) * | 2020-06-24 | 2020-09-15 | 西安眼得乐医疗科技有限公司 | Clinical decentration and tilt resistant intraocular lens |
Non-Patent Citations (1)
| Title |
|---|
| 基于Q-type 多项式的自由曲面表征函数及其在成像光学系统中的应用研究;李闯;中国优秀硕士学位论文全文数据库(第2018年第02期);18-25 * |
Also Published As
| Publication number | Publication date |
|---|---|
| CN113599021A (en) | 2021-11-05 |
Similar Documents
| Publication | Publication Date | Title |
|---|---|---|
| US20230355377A1 (en) | Extended depth of focus intraocular lenses and associated methods | |
| KR101864609B1 (en) | Ophthalmic lens with optical sectors | |
| EP2034928B1 (en) | Aspheric intraocular lens and method for designing such iol | |
| Pieh et al. | In vitro strehl ratios with spherical, aberration-free, average, and customized spherical aberration-correcting intraocular lenses | |
| KR101154066B1 (en) | Contrast-enhancing aspheric intraocular lens | |
| US20160100938A1 (en) | Toric lens with decreased sensitivity to cylinder power and rotation and method of using the same | |
| EP2062553A1 (en) | Optimal iol shape factors for human eyes | |
| US20160193040A1 (en) | Intraocular Lens System | |
| KR101842378B1 (en) | Ophthalmic lens for correcting astigmatism | |
| WO2010039839A1 (en) | Toric ophthalmic lenses having selected spherical aberration characteristics | |
| JP2007510521A (en) | Multi-zone intraocular lens for optical aberration correction | |
| KR20170056675A (en) | Multifocal intraocular lens with extended depth of field | |
| US20090059163A1 (en) | Ophthalmic Lens Having Selected Spherochromatic Control and Methods | |
| US20190076242A1 (en) | Methods of providing extended depth of field and/or enhanced distance visual acuity | |
| CN109363802A (en) | A kind of progressive modulation type aspheric intraocular lens of axial spherical aberration | |
| CN111658232A (en) | Clinical decentration and tilt resistant intraocular lens | |
| CN110613532B (en) | Posterior chamber type lens designed by toric surface | |
| US9089420B2 (en) | Intra ocular lens | |
| US20220287826A1 (en) | Intraocular lens providing extended depth of focus | |
| CN113599021B (en) | Aspherical intraocular lens for resisting postoperative residual refractive error | |
| CN112370212B (en) | Focal length adjusting method for combining intraocular lens with extraocular zooming | |
| US20200383775A1 (en) | Intraocular lens and methods for optimization of depth of focus and the image quality in the periphery of the visual field | |
| RU2785137C2 (en) | Intraocular lenses having optical structure shifted forward | |
| NL2005486A (en) | Intra ocular lens. |
Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| PB01 | Publication | ||
| PB01 | Publication | ||
| SE01 | Entry into force of request for substantive examination | ||
| SE01 | Entry into force of request for substantive examination | ||
| CB03 | Change of inventor or designer information | ||
| CB03 | Change of inventor or designer information |
Inventor after: Wang Mingkun Inventor after: Zhao Ziwei Inventor after: Zhang Mingrui Inventor after: Pei Xiujuan Inventor before: Wang Mingkun Inventor before: Zhao Ziwei Inventor before: Zhang Mingrui Inventor before: Pei Xiujuan |
|
| GR01 | Patent grant | ||
| GR01 | Patent grant |