METHOD, SYSTEM AND COMPUTER PROGRAM FOR MEASURING LIGHT DIFFUSION IN THE EYEBALL OR IN THE OCULAR REGION

Abstract

Method, system and computer program for measuring light diffusion in the eyeball or in the ocular region.

The method comprises: projecting a punctiform light beam onto the retina; correcting low-order ocular aberrations of the eye; capturing and recording an image of the retinal plane formed after reflection of the punctiform light beam on the retina and a double passage through the ocular media of the eye; and at the same time as capturing the image of the retinal plane, performing a high- and low-order ocular aberration measurement in the plane of the pupil and performing a light diffusion measurement, combining ocular aberration measurement information with information on the image of the retinal plane.

The system and the computer program are adapted for implementing the method.

Claims

1. A method for measuring light diffusion in the eyeball or in the ocular region, which comprises performing the following steps: projecting a punctiform light beam onto the retina of at least one eye of a patient; performing a first ocular aberrations measurement of said at least one eye of the patient and using the obtained results for correcting low-order ocular aberrations of said eye; and capturing and recording, once said low-order aberrations have been corrected, at least one image of a retinal plane formed after reflection of said punctiform light beam on the retina and a double passage through the ocular media of said eye; wherein the method comprises, at the same time as said capturing and recording performing a second high- and low-order ocular aberration measurement in a plane of the pupil of said eye, and further performing a light diffusion measurement, combining information obtained by means of said second high- and low-order ocular aberrations measurement with information of said image of the retinal plane.

2. The method according to claim 1, wherein it is implemented using open field techniques.

3. The method according to claim 1, wherein it is implemented in a binocular manner in both eyes of the patient.

4. The method according to claim 1, wherein it comprises performing said high- and low-order ocular aberration measurement on a wavefront coming from the reflection of said punctiform light beam on the retina, as it passes through the plane of the pupil.

5. (canceled)

6. The method according to claim 1, wherein it comprises using one and the same system for measuring aberrations for performing said first and second ocular aberration measurements.

7. The method according to claim 4, wherein it comprises analyzing the distribution of light of the image of the retinal plane and the distribution of light of an image corresponding to said ocular aberration measurement on said wavefront, in the plane of the pupil, and performing a light diffusion measurement by comparing both distributions of light.

8. The method according to claim 7, wherein it comprises analyzing said distribution of light for each of the light spots of both images.

9. The method according to claim 7, wherein it comprises applying respective optical transfer functions, termed OTF, to the ocular aberration measurement information and to the information on the image of the retinal plane, and performing a light diffusion measurement, combining the results provided by said OTF functions.

10. The method according to claim 9, wherein it comprises performing the light diffusion measurement, combining the results provided by said OTF functions and also by comparing both of said distributions of light.

11. The method according to claim 10, wherein said OTF functions include at least absolute values in respective modulation transfer functions, termed MTF, wherein the method comprises performing the light diffusion measurement, dividing values associated with profiles generated with said absolute values.

12. The method according to claim 11, wherein it comprises obtaining said values associated with said profiles, calculating the existing areas under the curves of said profiles, performing said division with the values calculated for said areas.

13. The method according to claim 10 wherein said OTF functions include complex argument values in respective phase transfer functions, or PTF.

14. The method according to claim 1, wherein said low-order aberrations include astigmatism and defocusing.

15. A system for measuring light diffusion in the eyeball or in the ocular region, comprising: means for projecting a punctiform light beam onto the retina of at least one eye (O1, O2) of a patient; means (CCD-DP1, CCD-DP2) for capturing and recording an image of a retinal plane formed after reflection of said punctiform light beam on the retina and a double passage through the ocular media of said at least one eye (O1, O2); and means (C1-2) for performing a first ocular aberrations measurement of said at least one eye of the patient and using the obtained results for correcting low-order ocular aberrations of said at least one eye (O1, O2) prior to said capturing and recording on the basis of the result of said first ocular aberrations measurement; the system further comprising: means (HS) for performing a second high- and low-order ocular aberrations measurement in a plane of the pupil of said eye (O1, O2); control means (MC) controlling at least said means (CCD-DP1, CCD-DP2) for capturing and recording an image of the retinal plane and also controlling said means (HS) for performing said second ocular aberrations measurement, so that they operate at the same time; and processing means (MP) processing, in a combined manner, information obtained by means of said second ocular aberrations measurement with information on said image of the retinal plane and providing, as a result of said processing, the value or values of said light diffusion measurement.

16. (canceled)

17. The system according to claim 15, wherein said means for projecting a punctiform light beam onto the retina of an eye of a patient and said means (CCD-DP1, CCD-DP2) for capturing and recording an image of the retinal plane are part of a double-pass ophthalmoscopic system.

18. The system according to claim 15 wherein it is configured and arranged for using open field techniques.

19. The system according to claim 15, wherein it is configured and arranged for implementing a binocular system applied to both eyes (O1, O2) of the patient.

20. The system according to claim 15, wherein said means (C1-2) for correcting low-order ocular aberrations comprise or are associated with said means (HS) for performing an ocular aberrations measurement, for said correcting of ocular aberrations depending on measurements taken with the means (HS) for performing an ocular aberrations measurement.

21. A computer program including code instructions which, when run in a computer, measure light diffusion in the eyeball or in the ocular region according to a method comprising: projecting a punctiform light beam onto the retina of at least one eye of a patient; performing a first ocular aberrations measurement of said at least one eye of the patient and using the obtained results for correcting low-order ocular aberrations of said eye; and capturing and recording, once said low-order aberrations have been corrected, at least one image of a retinal plane formed after reflection of said punctiform light beam on the retina and a double passage through the ocular media of said eye; wherein the method comprises, at the same time as said capturing and recording, performing a second high- and low-order ocular aberration measurement in the plane of the pupil of said eye, and further performing a light diffusion measurement, combining information obtained by means of said second high- and low-order ocular aberrations measurement with information of said image of the retinal plane, and processing, in a combined manner, data corresponding to the information obtained by means of measuring ocular aberrations with data corresponding to the information on the image of the retinal plane.

Description

BRIEF DESCRIPTION OF THE DRAWINGS

[0044] The foregoing and other advantages and features will be better understood based on the following detailed description of several embodiments making reference to the attached drawings, which must be interpreted in a non-limiting illustrative manner, in which:

[0045] FIG. 1 is a perspective view of a schematic depiction of the system proposed by the second aspect of the present invention for an embodiment in which an open field binocular system is implemented.

DETAILED DESCRIPTION OF SEVERAL EMBODIMENTS

[0046] According to the embodiment illustrated in FIG. 1, the system for measuring light diffusion in the eyeball or in the ocular region proposed by the second aspect of the present invention is an open field binocular system comprising means for projecting a punctiform light beam onto the retina of both eyes O1, O2 of a patient, which include a punctiform light source SLD generating a collimated (generally a laser light) beam which is distributed into two respective emission sub-beams by a mask or pupil P1, which are directed towards each of the two eyes O1, O2 by a series of common optical elements, particularly beam splitters BS1 and BS2 acting as mirrors and lenses L1 and L2, and after each of the emission sub-beams is redirected towards the respective eye O1, O2 by the mirror M1, each of them is individually directed by one of respective groups of optical elements, each of them formed particularly by a pair of cylindrical lenses C1-2 and C3-4, after which there are arranged another lens LL1 and LL2, another pupil P2 and P3, a respective mirror M2 and M4, another lens L3 and L5, a dichroic mirror DM1 and DM2 and, finally, a heat mirror HM1 and HM2, after which the emission sub-beam strikes the retina of the eye O1, O2.

[0047] FIG. 1 also shows how the system comprises means consisting of two cameras CCD-DP1y CCD-DP2, each of them provided for capturing and recording an image of the plane of one of the retinas, which image is formed after reflection of the two punctiform light emission sub-beams in the retina and a double passage through the ocular media of both eyes O1, O2, generating respective reflection sub-beams following a path opposite the emission sub-beam path, going through the optical elements to the beam splitter BS2, which reflects a portion of each of the reflection sub-beams, going through the lens L1 and the beam splitter BS1, after which each of the reflection sub-beams is directed to one of the cameras CCD-DP1 and CCD-DP2 by the mirror M3.

[0048] The pairs of cylindrical lenses C1-2 and C3-4 are part of or are means for correcting low-order ocular aberrations of the eyes O1, O2 prior to capturing and recording the images of the retinal planes.

[0049] In addition, FIG. 1 also shows how the system also comprises means for performing a high- and low-order ocular aberration measurement in the plane of the pupil of both eyes O1, O2, which particularly consists of a Hartmann-Shack sensor HS, which is struck by portions of the two reflection sub-beams going through the beam splitter BS2 and the lens L4.

[0050] FIG. 1 likewise illustrates, by means of arrows, the direction of the light in the first and second passage, i.e., the emission sub-beams towards the retinas and the reflection sub-beams in the opposite direction.

[0051] FIG. 1 also illustrates an electronic system SE communicated in a bidirectional manner with the cameras CCD-DP1, CCD-DP2 and the Hartmann-Shack sensor HS, and comprising control means MC controlling at least CCD-DP1, CCD-DP2 and HS so that they operate at the same time, and processing means MP processing, in a combined manner, information obtained by means of CCD-DP1, CCD-DP2 and HS and providing, as a result of said processing, the value or values of the light diffusion measurement.

[0052] For a non-illustrated embodiment, the control means MC are connected with the pairs of cylindrical lenses C1-2 and C3-4 (and/or with any other type of alternative mechanism suitable for correcting low-order ocular aberrations) to control them for the purpose of the mentioned correcting of ocular aberrations, depending on ocular aberration measurements taken with the Hartmann-Shack sensor HS.

[0053] A person skilled in the art could introduce changes and modifications in the described embodiments without departing from the scope of the invention as it is defined in the attached claims.