CREATION OF CURVED CUTS IN THE INDSIDE OF THE EYE CORNEA

Abstract

A device for isolating a lenticle in the cornea of an eye. The device includes: a laser beam source to emit pulsed laser radiation having a pulse frequency of 1.2 MHz to 10 MHz, a pulse energy of 1 nJ to 200 nJ and a wavelength penetrating the cornea; a beam-forming unit having beam optics with an image field and that bundles pulsed laser radiation into a focus located inside the image field, and which has a maximum diameter of less than 3 μm; a beam-deflection unit shifting the focus in the cornea and inside the image field, the focus moving along a path when the image field is resting; and a control unit to control the source and the beam-forming unit to isolate the lenticle by specifying the path. The lenticle is delimited by a cut surface which is curved with regard to a front surface of the cornea.

Claims

1. A device for generating a cut in the interior of an eye, the device comprising: a laser beam source that is designed to emit a raw train of laser radiation which penetrates a cornea of the eye, wherein each laser radiation pulse of the raw train is adapted to separate layers of material within the eye; a pulse picker which selects some laser radiation pulses of the raw train to provide a modified train of laser radiation pulses; a beam scanner which shifts the focus in the eye along a path to generate the cut by the modified train of laser radiation pulses emitted; and a processor, which is connected with the beam scanner and the pulse picker and is designed to control the beam scanner.

2. A method device for generating a cut in the interior of an eye, the method comprising: emitting a raw train of laser radiation pulses having a raw pulse frequency which penetrates a cornea of the eye; providing a modified train of laser radiation pulses adapted to separate layers of material within the eye; and shifting a focus in the eye along a path to generate the cut by the modified train of laser radiation pulses emitted.

Description

BRIEF DESCRIPTION OF THE FIGURES

[0050] The invention is explained by way of example in yet greater detail in the following with reference to the attached drawings, which also disclose features essential to the invention. There are shown in:

[0051] FIG. 1 a schematic representation of a device for carrying out a lenticle-extraction correction of impaired vision,

[0052] FIG. 2 a simplified sectional representation through the cornea of an eye to illustrate the lenticle to be isolated and extracted, and

[0053] FIG. 3 a projection of a cut surface delimiting the lenticle, to illustrate the creation of the cut surface.

DETAILED DESCRIPTION

[0054] FIG. 1 shows, schematically, a device 1 for carrying out a lenticle-extracting correction of impaired vision. Device 1 has a laser 2 which provides pulsed laser radiation, wherein in the embodiment outlined, the laser 2 emits a pulsed pure beam 3 which has a wavelength which penetrates into the tissue of the cornea of an eye, with the result that a machining by means of non-linear effects can take place there. Pure beam 3 is shaped by a chopper 4 with regard to pulse duration, wherein predistortion known from the state of the art can take place, which ensures that the desired pulse length of for example ≤1 ps is present after passing through the further optical path of the beam path in the material, i.e., in the cornea of an eye. Chopper 4 and laser 2 form a laser beam source 5 which emits a pulsed laser beam 6 of the desired pulse length.

[0055] Pulsed laser beam 6 also passes through a scanner 7 which preferably brings about a two-dimensional deflection transverse to the direction of propagation of the laser radiation. The laser beam 6 scanned in this way is focused into the cornea of an eye by an objective 8. Scanner 7 forms a beam forming unit 9 together with the objective 8, which ensures that pulsed laser radiation 6 is focused into a cornea of an eye in locations which can be set, wherein the focus diameter there is less than 3 μm.

[0056] Laser beam source 5 can optionally comprise a so-called pulse picker which can for example be part of the chopper 4. This pulse picker changes the frequency of the laser radiation pulses in the pure beam 3, which pulses have a machining effect on the cornea of an eye. Thus for example it is possible to design the laser 2 such that it provides a pure beam 3 with a pulse frequency which is clearly higher than that pulse frequency which is desired for the machining-effective laser pulses of the laser beam 6. Then, the pulse picker reduces the frequency of the effective laser radiation pulses by rendering the machining effect of individual laser radiation pulses harmless. This can for example take place by the pulse picker increasing the pulse length. The importance of the pulse picker known in the state of the art will be explained later on with the help of FIG. 3.

[0057] In the embodiment shown in FIG. 1, the pulse frequency of the pulsed laser beam 6 is between 1.2 MHz and 10 MHz, wherein the frequency is relative to those pulses which have a machining effect, i.e., pulses which are not rendered harmless by a pulse picker if present.

[0058] The energy of these pulses of the pulsed laser beam 6 is between 1 nJ and 200 nJ, preferably between 10 nJ and 100 nJ, particularly preferably between 20 nJ and 80 nJ.

[0059] The wavelength of laser beam 6 lies in a range of 1030 nm to 1060 nm or 300 nm to 400 nm or another spectral range which can penetrate into the cornea, for which the cornea thus has a transmission factor of at least 0.8.

[0060] Device 1 also comprises a contact lens 10 which serves to fix the eye 11 and also to give the front surface of the cornea 12 of an eye 11 a desired and known shape. The corresponding contact surface of contact lens 10 has a radius of curvature of 50 mm or less, particularly preferably 20 mm or less, for this purpose.

[0061] Objective 8 bundles the laser radiation 6 into a focus 13 which is inside the cornea 12. Focus 13 has a maximum diameter of 3 μm, preferably a maximum of 2 μm. The maximum diameter is the largest diameter which, e.g., in the event of an elliptical focus spot, is measured along the large semiaxis. In the event of a circular spot, the spot diameter is the relevant measurement.

[0062] The dotted line of FIG. 1 shows that, depending on the effect of the scanner 7, the focus 13 is at different points in the cornea 12 of an eye 11. In the design of FIG. 1, the scanner 7 brings about a deflection transverse to the main direction of incidence of the laser radiation 6. The focus position is adjusted along the main direction of incidence by suitable actuation of the objective 8, which is designed to be suited to a z-adjustment.

[0063] The laser beam source 5 (in the design of FIG. 1 produced by laser 2 and chopper 4) as well as the beam forming unit 9 (in the design of FIG. 1 produced by scanner 7 and objective 8) are connected to a control apparatus 14 via control lines, not shown in more detail, which control apparatus controls these elements in suitable manner. The actuating of the control apparatus 14 creates a cut surface in the cornea of an eye. The corresponding relationships are represented in a sectional representation in FIG. 2, which shows the cornea 12 schematically.

[0064] A lenticle 15 in the cornea 12 is isolated by adjusting the focus 13 of the pulsed laser radiation 6. Lenticle 15 is delimited at the front by a flap surface 16 and at the back by a lenticle surface 17. In order to be able to keep the boundary surfaces of the lenticle 15 as simple as possible, the flap surface 16 is at a uniform distance from the front surface 18 of cornea 12. Flap surface 16 is thus not curved with regard to front surface 18. This is different in lenticle surface 17 which is curved with regard to the front surface 18. Without such a curvature, the removal of the lenticle 15 would not change the curvature of the front surface 18 of the cornea 12. If the lenticle 15 is removed, however, the lenticle surface 17, curved with regard to front surface 18, changes the curvature of the front surface 18 of the cornea 12. This is removed by a lateral cut, not shown in FIG. 2, which cut for example leads at the edge of lenticle 15 from the flap surface 16 to the front surface 18 and makes it possible for the isolated lenticle 15 to be extracted, optionally after reduction of the material of the lenticle 15. In the representation of FIG. 2, flap surface 16 and lenticle surface 17 are symmetrical to the optical axis OA. This is set automatically for flap surface 16 if it has a uniform distance from front surface 18.

[0065] The boundary surfaces of the lenticle 15 may naturally also comprise further surfaces apart from flap surface 16 and lenticle surface 17. For example, with a lenticle 15 which is thinner on the optical axis OA than in regions far away from the axis, an additional edge surface can be provided which connects flap surface 16 to lenticle surface 17, which then has a more curved path than flap surface 16 and front surface 18.

[0066] The cut surfaces for isolating the lenticle 15 are thereby created by the focus 13 being shifted along a path which lies in the corresponding surface. This is shown by way of example in FIG. 3 with the help of lenticle surface 17 which, for reasons of clarity, is elliptical here. This is intended to show that device 1 can be used to correct not only a spherical visual defect but also an astigmatism. Basically, during higher-aberration corrections, lenticle 15 is no longer rotation-symmetrical to the optical axis OA. FIG. 3 shows a folding-up of the lenticle surface 17 in the drawing plane. In FIG. 3, a path 19 is drawn in using a dotted line. The position of the focus 13 is adjusted along this path. Generally, naturally not just one adjustment transverse to the optical axis OA is necessary, but also an adjustment of the focus position along the optical axis OA. This therefore cannot be seen in FIG. 3, as this figure shows a folding-up of the lenticle surface 17 in the drawing plane, which is why, in the representation of FIG. 3, path 19 lies in a plane. By looking at the cut through lenticle 15 in FIG. 2 it becomes clear that, the greater the distance from the optical axis OA, the further away from the front surface 18 the z-position of the focus is shifted.

[0067] Targets 20 are drawn in along the path 19 of FIG. 3. In each case they indicate a point at which a laser pulse of the pulsed laser radiation 6 is emitted. The lenticle surface 17 is designed as a cut surface overall by arranging the targets 20 in series along the path 19 and by a suitable choice of the path 19. The distances between targets 20 are chosen such that the fewest possible material bridges remain, meaning that the lenticle surface 17 is thus generated entirely as a cut surface.

[0068] With the help of FIG. 3 it can easily be understood why it is advantageous to make it possible to change the pulse frequency of the pulsed laser beam 6. If it were desired to arrange the targets 20 to be as equidistant as possible, the pulse frequency and the shift speed of the beam forming unit 9 can be adapted to one another. As a high pulse frequency laser 2 can generally be adjusted only at great expense, it is advantageous to provide firstly a pure beam 3 with the laser 2, which pure beam has a pulse frequency which is greater than or equal to the maximum pulse frequency desired for the laser beam 6. It may be easier to produce such a laser 2 and to combine same with a pulse picker than to design a laser with a pulse frequency which can be directly adjusted. Thus the pulse frequency can be adapted to the shift speed, and the time taken to create cut surfaces is reduced.

[0069] The parameters for pulse energy, pulse frequency, focus diameter and optionally pulse length, named in the description of the figures as well as in the general part of the description, lead to the cut surfaces being created with a mechanism for separating tissue which uses tissue cutting and essentially tissue splitting to their full capacity. Thus a desired position for the delimiting cut surfaces of the lenticle 15 can be produced with great precision.