METHOD OF CORRECTING HIGHER-ORDER ABERRATIONS USING LASER VISION CORRECTION

Abstract

The disclosure provides a method for correcting higher-order aberrations including providing a laser radiation. The method also includes controlling a location of a beam focal point of the laser radiation by a system of scanners and guiding the beam focal point in such a way that the location of the beam focal point is in a cornea of an eye. The method further includes introducing the laser radiation into the cornea of the eye. The method includes cutting a lenslet, wherein a thickness of the lenslet t(X,Y) satisfies a following equation: t(X,Y)=t.sub.0+t(X,Y)/(n1), where t(X,Y) represents a higher-order wavefront elevation and t.sub.0 represents the thickness of the lenslet having a spherical refractive power of D.

Claims

1.-20. (canceled)

21. A method for correcting higher-order aberrations, comprising: obtaining a curve of an initial surface (R) of a lenslet to facilitate spherical correction of refractive error in an eye; controlling a location of a beam focal point of laser radiation by a system of scanners and guiding the beam focal point in such a way that the location of the beam focal point is in a cornea of the eye; and cutting the lenslet according to a final surface of the lenslet, the final surface of the lenslet varied from the curve of the initial surface (R) of the lenslet to correct the higher-order aberrations, comprising: determining a variation in a radius to reach the final surface of the lenslet; and varying the system of scanners to achieve the variation.

22. The method of claim 21, wherein the varying the system of scanners includes varying one or more scanners in an x-y plane rather than a z-direction to achieve the variation.

23. The method of claim 21, wherein the varying the system of scanners includes moving the beam focal point in a z-direction 10 micrometers (m) or less in one circumference around the lenslet.

24. The method of claim 21, wherein the variation in the radius to reach the final surface of the lenslet at any X,Y point satisfies a following equation: $r\left(X,Y\right)=t\left(X,Y\right)*R/r$ where t(X,Y) represents a higher-order wavefront elevation, R represents the curve of the initial surface of the lenslet, and r/R represents a slope of the curve R at a position of r on the curve R.

25. The method of claim 21, wherein the laser radiation is a femtosecond laser.

26. A method for correcting higher-order aberrations, comprising: providing a laser radiation; controlling a location of a beam focal point of the laser radiation by a system of scanners and guiding the beam focal point in such a way that the location of the beam focal point is in a cornea of an eye; introducing the laser radiation into the cornea of the eye; and cutting a lenslet via the laser radiation, a cross-section of the lenslet showing an anterior lenslet surface having a plurality of convex curves and having a plurality of concave curves, each convex curve of the plurality of convex curves being convex relative to an anterior corneal surface, each concave curve of the plurality of concave curves being concave relative to the anterior corneal surface.

27. The method of claim 26, wherein the laser radiation is provided by a femtosecond laser.

28. The method of claim 26, wherein the system of scanners comprises at least one transverse control element operating in an x-y plane orthogonal to a direction of the laser radiation and at least one longitudinal control element operating in a z-direction.

29. The method of claim 26, wherein the higher-order aberrations are expressed using Zernike, Fourier, wavelet, Wiegner, or other orthogonal polynomials.

30. The method of claim 26, wherein the lenslet is cut using a spiral scanning of the laser radiation.

31. The method of claim 26, wherein the system of scanners includes a 3D scanner.

32. A pulse laser device for correcting higher-order aberrations, comprising: a laser source that provides a laser radiation; a system of scanners configured to control a location of a beam focal point of the laser radiation; and a computing device configured to perform operations comprising: obtaining a curve of an initial surface (R) of a lenslet to facilitate spherical correction of refractive error in an eye; instructing the system of scanners to control a location of a beam focal point of the laser radiation in such a way that the location of the beam focal point is in a cornea of the eye; and guiding the laser radiation to cut the lenslet according to a final surface of the lenslet, the final surface of the lenslet varied from the curve of the initial surface (R) of the lenslet to correct the higher-order aberrations, the operation of guiding the laser radiation comprising: determining a variation in a radius to reach the final surface of the lenslet; and instructing the system of scanners to guide the laser radiation according to the determined variation.

33. The pulse laser device of claim 32, wherein the instructing the system of scanners to guide the system of scanners includes varying one or more scanners in an x-y plane rather than a z-direction to achieve the variation.

34. The pulse laser device of claim 32, wherein the instructing the system of scanners to guide the system of scanners includes instructing the system of scanners to move the beam focal point 10 micrometers (m) or less in a z-direction in one circumference around the lenslet.

35. The pulse laser device of claim 32, wherein the variation in the radius to reach the final surface of the lenslet at any X,Y point satisfies a following equation: $r\left(X,Y\right)=t\left(X,Y\right)*R/r$ where t(X,Y) represents a higher-order wavefront elevation, R represents the curve of the initial surface of the lenslet, and r/R represents a slope of the curve R at a position of r on the curve R.

36. The pulse laser device of claim 32, wherein the higher-order aberrations are measured with a wavefront meter or a corneal topographer.

37. The pulse laser device of claim 32, wherein the system of scanners includes at least one transverse control element to move the beam focal point in an x-y plane and at least one longitudinal control element to move the beam focal point in a z-direction.

38. The pulse laser device of claim 32, wherein the higher-order aberrations are represented by Zernike or Fourier polynomials.

39. The pulse laser device of claim 32, wherein the lenslet is cut using a spiral scanning of the laser radiation.

40. The pulse laser device of claim 32, wherein the system of scanners includes a 3D scanner.

Description

BRIEF DESCRIPTION OF THE DRAWINGS

[0027] Embodiments of the present disclosure are described by way of example in greater detail with reference to the attached figures, which are not necessarily to scale, and in which:

[0028] FIG. 1 is a schematic diagram of a pulsed laser system;

[0029] FIG. 2A is an illustration of a cross-sectional view of a cornea depicting a lenslet cut geometry for a small incision lenslet extraction procedure;

[0030] FIG. 2B is an illustration of a cross-sectional view of a cornea depicting a lenslet cut geometry for a small incision lenslet extraction procedure with respect to axes;

[0031] FIG. 3 illustrates aberration modes based on Zernike polynomial functions;

[0032] FIG. 4A is an illustration of a cross-sectional view of a cornea depicting a lenslet cut geometry for higher-order aberrations;

[0033] FIG. 4B is an illustration of a cross-sectional view of cornea depicting a lenslet cut geometry for higher-order aberrations with respect to axes;

[0034] FIG. 5 is a schematic plan view of a cornea illustrating a lenslet cutting geometry for higher-order aberrations;

[0035] FIG. 6 illustrates wavefront elevation maps generated from a wavefront meter and corneal topographer;

[0036] FIG. 7 illustrates a method for correcting higher-order aberrations; and

[0037] FIG. 8 illustrates another variation of the method for correcting higher-order aberrations.

DETAILED DESCRIPTION

[0038] Embodiments of the present disclosure are directed to laser vision correction. More particularly, embodiments of the present disclosure are directed to a method of cutting a lenslet (a portion of the cornea that is removed during vision correction surgery and also called a lenticule) using a femtosecond laser to correct higher-order aberrations (HOAs). Embodiments of the present disclosure allow for correcting HOAs without creating a flap by cutting through the corneal epithelium and Bowman's membrane with a femtosecond laser.

[0039] FIG. 1 is a schematic diagram of a pulsed laser system 100 for eye surgery, including refractive eye surgery such as laser vision correction. The pulsed laser system 100 may be a separate surgical tool, or part of a larger eye surgery system, which may include other laser systems, patient or eye positioning systems, viewing systems, or any combinations thereof. In particular, the pulsed laser system 100 may be part of a surgical suite designed to provide substantially all computer-assisted devices for performing a given eye surgery.

[0040] A pulsed laser system 100 includes a laser source 102, which generates laser radiation 104. The laser radiation 104 (a laser beam) may include laser radiations used to cut eye tissues including such as corneal stroma through vaporization (a laser scalpel). For example, the laser radiation 104 generated from the laser source 102 may include a femtosecond, picosecond, nanosecond, or attosecond laser.

[0041] A pulsed laser system 100 includes a scanner 106 for controlling a radiation focal points 108 during surgery in the cornea of the patient's eye. The scanner 106 provides transverse control axis (X- and Y-axes), longitudinal control axis (Z-axis) of radiation focal points 108. Transverse refers to a direction at a right angle to the propagation direction of laser beam 104. Longitudinal refers to the propagation direction of the laser beam 104. The scanner 106 may be 3D scanner.

[0042] Although the pulsed laser system 100 in FIG. 1 does not show various other radiation control components, the scanner 106 may control radiation focal points 108 in a longitudinal direction using a longitudinal control element. For example, longitudinal control element may include a longitudinally adjustable lens. Alternatively, longitudinal control element may include a variable refractive power lens. Also, alternatively, longitudinal control element may include a deformable mirror. Further, the scanner 106 may contain more than one transverse control element, more than one longitudinal control element, or more than one of both. In addition, the transverse control element and the longitudinal control element may be separate devices. Although scanner 106 shown in FIG. 1 is depicted as one component, such a configuration is merely provided for illustrative purposes. The embodiments of the present disclosure may be configured to include multiple scanners (a system of scanners) to allow for more precise control of the radiation focal points 108.

[0043] The laser source 102 and scanner 106 are controlled by computer 110. For example, the computer 110 may control which wavelength of laser radiation 104 is generated from the laser source 102. For instance, the computer may configure the laser source 102 to generate a femtosecond laser 104. Further, the computer 110 may control the length of the laser radiation 104. Additionally, the computer 110 may control the scanner 106 to change movements of the radiation focal points 108.

[0044] The computer 110 includes at least a processing resource able to execute code to generate instructions to control a lenslet cut geometry and a lenslet cut location in the cornea of a patient's eye. The computer 110 may be in physical or wireless communication with laser source 102 and scanner 106. The computer 110 may further include a memory, particularly a memory for storing instructions for the processing resource, a communications module for communicating with laser source 102 and scanner 106, and other components.

[0045] For simplicity, not all potential components of the pulsed laser system 100 are illustrated in FIG. 1. For example, the pulsed laser system may include various components for directing, focusing, or otherwise manipulating laser beam, such as scanners, mirrors, beam expanders, or lenses. The pulsed laser system 100 may further include housings and other equipment to protect and position its components as well as patient-interface peripherals, which may be disposable.

[0046] Referring now to FIG. 2A, a schematic depiction 200 of cut geometry for a small incision lenslet extraction procedure (such as SMILE) is described. The human eye has a cornea, which is a transparent front part of the eye that covers the iris, pupil, and anterior chamber. For laser vision correction surgery, a portion of stroma (such as lenslet 210) within the cornea is removed to change a thickness of the patient's cornea to correct vision. The schematic depiction of cut geometry shown in FIG. 2A is a cross-sectional view of a cornea of a human eye. In general, for a SMILE procedure, a lenslet 210 is created with a femtosecond laser in a shape corresponding to a desired refractive correction. The femtosecond incisions for the SMILE procedure include four cuts: 1) cornea posterior cut; 2) side cut for the lenslet; 3) cap cut; and 4) side cut for the opening incision. The four cuts are performed in succession in an integrated manner. Then, the lenslet is subsequently accessed and removed through the opening incision. The cornea includes anterior cornea 202 and posterior cornea 204. The lenslet cut creates anterior spherical surface 206 of the lenslet 210 and posterior spherical surface 208 of the lenslet 210.

[0047] Referring now to FIG. 2B, a schematic depiction 250 of cut geometry for small incision lenslet extraction procedure (such as SMILE) with respect to X-, Y-, and Z-axes is described. The lenslet is cut using a femtosecond laser. The spatial position of the laser radiation is controlled by three scanners: X-, Y-, and Z-scanners.

[0048] In general, X and Y scanners are galvanometric scanners. The lenslet is cut using spiral scanning of the femtosecond laser beam. The spiral is typically nearly a circle, because the radial line separation of consecutive spirals is around 5 um and the radius of the scanning is several thousand microns. For example, a diameter of a circle may be 4 mm (such as 4000 m). Thus, the next outer circle of the spiral would have a diameter of 4010 m.

[0049] The spherical refractive power of the lenslet is determined by the radii of the curvature of the anterior R1 and posterior R2 curvature of the lenslet surface as defined by the following equation:

[00001]$\begin{array}{cc}D=\left(n-1\right)*\left(1/R2-1/R1\right)& \left(\mathrm{eq}1\right)\end{array}$

where D is the spherical refractive power of the lenslet and n is the refractive index of the cornea.

[0050] A thickness of the lenslet t.sub.0 at the radial position r can be calculated by the following equation:

[00002]$\begin{array}{cc}{t}_0=0.5*r^2\left(1/R2-1/R1\right)=\left(r^2/2\right)*D/\left(n-1\right)& \left(\mathrm{eq}2\right)\end{array}$

[0051] The Z scanner is typically an axially adjustable telescope. Due to mechanical inertia the Z scanner is slow and not able change position, speed, or acceleration nearly as rapidly as the scanners movable in the x and y planes. However, the circle time of scanning in Z axis is about 20 ms and within 20 ms, the Z position can be moved by a few microns, allowing the lenslet to be cut with a spherical shape.

[0052] Surfaces derived from a high order azimuthal Zernike polynomial presently cannot be cut using the Z scanner of femtosecond laser, since the rotation time of =5 mm circle having a typical 5 m spot separation at 150 kHz laser rep rate=T=5000*/(5*150000)=21 ms. Within 21 ms the Z scanner is incapable of moving up and down several times to cut a high order azimuthal surface.

[0053] Now referring to FIG. 3, aberration modes based on Zernike polynomial functions are illustrated. Aberrations are focusing errors that prohibit the formation of high resolution. One of the ways to characterize the aberrations includes wavefront aberrations, which characterizes complex optical errors in focus produced by an optical system. The Zernike polynomial series is used to decompose complex wavefront aberrations into a collection of polynomial basis functions (such as modes), which are shown in FIG. 3.

[0054] Each Zernike mode includes two components: 1) radial order (n) and 2) meridional frequency (f). In ophthalmology, radial orders of Zernike polynomial series are categorized as either low-order aberrations or high-order abrasions. Low-order aberrations are Zernike modes having second order or lower (n2). High-order aberrations are Zernike modes having third order or higher (n3). Low-order aberrations which correspond to Zernike defocus (4 in FIG. 3) and astigmatism modes (3 and 5 in FIG. 3) are typically corrected with prescription spectacle lenses or contact lenses, while correction of high-order aberrations requires more complex procedures. The higher the radial order and/or meridional frequency is, the more complex a Zernike polynomial mode becomes. Cutting a lenslet for one of the high-order aberrations which is shown in FIG. 3 is an arduous task with a slow z scanner of the femtosecond laser.

[0055] Now referring to FIG. 4A, an illustration depicting a lenslet cut geometry, in accordance with one or more embodiments of the present disclosure is shown. The schematic depiction of cut geometry shown in FIG. 4A is a cross-sectional view of a cornea. In one embodiment, the lenslet 410 which corrects for high-order aberrations may be cut. For example, the lenslet 410 may include multiple high-order Zernike polynomial modes. In this regard, the lenslet 410 does not simply have a spherical shape such as shown in FIGS. 2A and 2B. The cornea includes anterior cornea 402 and posterior cornea 404. The lenslet cut 410 creates anterior spherical surface 406 of the lenslet 410 and posterior spherical surface 408 of the lenslet 410.

[0056] In some embodiments, a thickness of the lenslet 410 which corrects higher-order aberrations can be calculated and a surface of the lenslet having a radius of curvature R is cut as follows:

[0057] The typical radial separation of two consecutive spiral cut RS is about 5 m. To have a radius of curvature of the lenslet surface R, the vertical step (VS) should be

[00003]$\begin{array}{cc}\mathrm{VS}=r/R*\mathrm{RS}& \left(\mathrm{eq}3\right)\end{array}$

where r/R is the slope of the R surface at the position of r. To correct the HOA, the thickness of the lenslet should be changed to

[00004]$\begin{array}{cc}t\left(X,Y\right)=t_0+t\left(X,Y\right)/\left(n-1\right)& \left(\mathrm{eq}4\right)\end{array}$

where t(X,Y) is the HOA wavefront elevation measured with the wavefront meter or corneal topographer. It is noted that t.sub.0 is the thickness of the lenslet having a spherical refractive power of D which is responsible for correcting the spherical error. It is further noted that t(X,Y) is responsible for correcting the HOAs. t(X,Y) is typically described either with Zernike or Fourier polynomials.

[0058] FIG. 4B is an illustration depicting a lenslet cut geometry for higher-order aberrations with respect to axes, in accordance with one or more embodiments of this disclosure. As described in FIG. 4B, it is noted that by increasing the radius of the scanning by r the thickness of the lenslet is increasing by

[00005]$\begin{array}{cc}t=r*\left[\mathrm{slope}\mathrm{of}\mathrm{the}R\mathrm{surface}\right]& \left(\mathrm{eq}5\right)\end{array}$

where the slope of the R curve is r/R, for example. Then, t may be expressed as

[00006]$\begin{array}{cc}t=r*r/R& \left(\mathrm{eq}6\right)\end{array}$

Thus, in order to correct the HOA, the radius on the scanning at any X,Y point should be increased by

[00007]$\begin{array}{cc}r\left(X,Y\right)=t\left(X,Y\right)*R/r& \left(\mathrm{eq}7\right)\end{array}$

[0059] FIG. 5 is a schematic plan view 500 of a cornea illustrating a lenslet cutting geometry, in accordance with one or more embodiments of the present disclosure. In one embodiment, in order to correct the HOA, the radius on the scanning at any X,Y point may be increased by r(X,Y)=t(X,Y)*R/r, as described hereinbefore. Since radial scanning with X- and Y-axes scanners is fast, cutting the lenslet geometry including high-order aberrations may not need a change in Z-coordination. Therefore, embodiments of the present disclosure may allow for correcting the HOA without rapidly changing Z-coordinate when scanning.

[0060] FIG. 6 is illustrations of wavefront elevation maps (600 and 650) generated from wavefront meter or a corneal topographer. In one embodiment, a calculation of radius on the scanning at any X,Y point r(X,Y) to correct the HOA may require a wavefront elevation map using a wavefront meter or a corneal topographer. Wavefront elevation maps reveal any irregularity of corneal surface.

[0061] FIG. 7 illustrates a method for correcting higher-order aberrations, in accordance with one or more embodiments of the present disclosure. The pulse laser device for correcting higher-order aberrations used in this method may be described in FIGS. 4A-5. It is noted that all of the steps shown in FIG. 7 are not essential to practice the method. One or more steps may be omitted from or added to the method illustrated in FIG. 7, and the method can still be practiced within the scope of this embodiment.

[0062] The method shown in FIG. 7 generally includes providing a laser radiation. The method further includes controlling a location of a beam focal point of the laser radiation by a scanner and guiding the beam focal point in such a way that the location of the beam focal point is in a cornea of an eye. The method further includes introducing the laser radiation into the cornea of the eye. The method further includes cutting a lenslet, wherein a thickness of the lenslet t(X,Y) satisfies a following equation:

[00008]$\begin{array}{cc}t\left(X,Y\right)=t_0+t\left(X,Y\right)/\left(n-1\right)& \left(\mathrm{eq}4\right)\end{array}$

where t(X,Y) represents a higher-order wavefront elevation and t.sub.0 (eq 2) represents the thickness of the lenslet having a spherical refractive power of D.

[0063] FIG. 8 illustrates another variation of the method for correcting higher-order aberrations, in accordance with one or more embodiments of the present disclosure. The pulse laser device for correcting higher-order aberrations used in this method may be described in FIGS. 4A-5. It is noted that all of the steps shown in FIG. 8 are not essential to practice the method. One or more steps may be omitted from or added to the method illustrated in FIG. 8, and the method can still be practiced within the scope of this embodiment.

[0064] The method shown in FIG. 8 generally includes providing a laser radiation. The method further includes controlling a location of a beam focal point of the laser radiation by a scanner and guiding the beam focal point in such a way that the location of the beam focal point is in a cornea of an eye. The method further includes introducing the laser radiation into the cornea of the eye. The method further includes cutting a lenslet, wherein a radius of the lenslet at any X,Y point satisfies a following equation:

[00009]$\begin{array}{cc}r\left(X,Y\right)=t\left(X,Y\right)*R/r& \left(\mathrm{eq}7\right)\end{array}$

where t(X,Y) represents a higher-order wavefront elevation, R represents a curvature of the cornea, and r/R represents a slope of the curvature of the cornea.

[0065] Although this disclosure has been described in terms of certain embodiments, modifications (such as substitutions, additions, alterations, or omissions) of the embodiments will be apparent to those skilled in the art. Accordingly, modifications may be made to the embodiments without departing from the scope of the invention. For example, modifications may be made to the systems and apparatuses disclosed herein. The components of the systems and apparatuses may be integrated or separated, and the operations of the systems and apparatuses may be performed by more, fewer, or other components. As another example, modifications may be made to the methods disclosed herein. The methods may include more, fewer, or other steps, and the steps may be performed in any suitable order.