KR20160140590A - Portable wavefront aberrometer - Google Patents

Abstract

A module for use with a mobile device for measuring aberrations of a patient's eye includes a light source having a proximal end and a distal end, and a light source. The optical shaft includes a plurality of first optical components arranged to direct light along a first optical path from a light source to a proximal end and a second optical component arranged to direct light along a second optical path from the proximal end to the optical detector of the mobile device And a plurality of second optical components. The connector at the distal end includes at least one guide element for positioning the distal end adjacent the photodetector. When the distal end is positioned adjacent the photodetector, the plurality of first optical components direct the light along the first optical path and the second plurality of optical components direct the light along the second optical path.

Description

[0001] PORTABLE WAVEFRONT ABERROMETER [0002]

relation Cross reference to application

The present application claims the benefit of priority of U.S. Provisional Patent Application No. 61 / 922,337, filed December 31, 2013.

Technical field

An embodiment of the present disclosure relates to an optical apparatus for detecting and measuring refractive errors in a patient's eye.

In the United States, vision tests are not routinely offered to children under the age of six, and only 14 percent of children under six receive a vision test. In addition, more than 500 million people around the world suffer from refractory-related diseases, and more than 90% of these people are in developing countries. This condition is likely to deteriorate over time if not initially identified and calibrated.

Due to a number of factors both initial and general detection may not be achieved. One is communication, in the case of a child who can not express clearly that he / she is experiencing the disease, or in a developing country where the patient may not be able to communicate effectively with the health care provider. Another factor is cost, which can be particularly limited in developing countries because equipment to detect refractive errors can be expensive and well-trained personnel to operate equipment and analyze results can have inaccessible or limited availability have.

The present disclosure is illustrated by way of example, and not by way of limitation, in the figures of the accompanying drawings in which like references represent similar elements.
Figure 1 shows an array of lenses that focus the light on a wavefront produced by the light reflected from the eye, the retina of the eye, and the light detector of the mobile device camera.
Figure 2 shows the design of the disclosed wavefront aberration system.
Figure 3 shows an alternative design of the disclosed wavefront aberration system.
Figure 4 shows the difference in Shack-Hartmann spots corresponding to the eye with normal eye and refractive error, and the wavefront contour shape showing defocus and astigmatism.
5 is an illustration of an implementation of a module and associated mobile device.
6A shows a view of an exemplary module in use according to an embodiment.
Figure 6B illustrates another aspect of an exemplary module in use in accordance with an embodiment.
Figure 7 is an exemplary process for measuring aberrations in a patient's eye using any of the embodiments disclosed herein.

The subject matter of this application relates to diagnostic equipment most commonly used by ophthalmologists and optometrists to detect and measure refractive errors in a patient's eye. More particularly, the subject matter of this application relates to a module that can be reversibly attached to a portable computing device, such as a smart phone, thereby creating a functional wavefront aberration system. The gist of the present application utilizes a light source, for example a laser present on the module, to produce light to be reflected from the eye. In addition, the disclosed apparatus captures this reflected light using a camera of a portable computing device, which can then be translated by the software of the portable computing device and provided for use by medical professionals and others.

One object of the present disclosure is to provide a module for generating a functional wavefront aberration when reversibly coupled to a portable computing device such as a smartphone. A further object is to provide a lower cost wavefront aberration by using a portable computing device that is already potentially owned by the consumer. Another object is to provide a lower cost wavefront aberration module that can be rented to a patient for use by an optical specialist for use in providing multiple data sets that are commoditized and tracked by the optical specialist to a change beyond the refraction of the patient's eye . Another object is to commercialize by an optical specialist and loan it to a patient so that the patient can obtain refractive measurements without visiting an optical specialist and, optionally, to pass these measurements to an optical specialist for diagnostic or screening purposes, Cost module that allows calibration lenses to be fitted or otherwise purchased. ≪ RTI ID = 0.0 > [0002] < / RTI > As the characteristics of the embodiments disclosed herein may reduce costs associated with the wavefront aberration system, this may be a device that is executable in the home or in a region where medical infrastructure is limited, for example in a developing country.

This object can be obtained by a wavefront aberration module ("module") that can be reversibly attached to a mobile computing device ("mobile device"), e.g., a smartphone, personal digital assistant, laptop or palmtop computer. A smartphone is a mobile phone having a computer, a glowing screen, and a camera among other configurations. Other mobile devices having cameras may be used in accordance with the teachings of the present application. For example, a mobile device that may be used in accordance with the disclosed implementation may be a phone (or smartphone) with a camera, but other devices such as tablet computers, laptop computers, specific audio or video players, And all of which may include a photodetector (e.g., a camera) and a transceiver for communicating information captured by the central processing unit or camera to the central processing unit. To provide a beam path through which light from a light source that is reflected from a patient's eye travels through an array of microlenses to a photodetector, in order to provide a beam path through which the light from the light source may point toward the patient's eye , The module may include a guide for positioning or attaching the module to the mobile device.

The gist of the present application separates certain components of the wavefront aquifer into two components that can be connected to form a functional unit. One component, a module, is a system that directs light reflected from a patient's eye to a photodetector that ultimately includes a portion of the mobile device, through a system that focuses and directs light to the patient ' s eye, and through an array of lenses . This separation allows for the main benefit of the subject matter of the present application, which is to divide the cost and complexity of the wavefront aberration to create a module part and a mobile device part, the part of the mobile device possibly being owned by the consumer, It is possible.

In use, the module is reversibly attached to the mobile device and held in place such that the light beam from the light source of the module is focused by the module onto the wearer's eye. When in place, the light source of the module, which will ultimately be scattered by the wearer's retina and passing through the microlens array, is activated before being detected by the camera of the mobile device. The data collected by the camera may then be processed by a microcomputer of the mobile device through an algorithm known in the art or the data may be passed to a different computer for processing by the mobile device. The data may be presented to the end user in an untreated form or may be presented in a post-processing format, such as a glasses prescription or a Snellen fraction. The software of the mobile device may also limit the information presented to the end user and transmit unprocessed or processed data to the optical specialist for diagnostic use and / or preparation of the corrective lens.

Certain embodiments of the disclosure relate to a module for use with a mobile device for measuring aberrations in a patient's eye. In one aspect, the module includes a light shaft having a proximal end and a distal end. The optical shaft includes a plurality of first optical components arranged to direct light along a first optical path from a distal end to a proximal end and a plurality of first optical components arranged to direct light along a second optical path from the proximal end to the distal end, And a second optical component. In some embodiments, at least some of the first and second optical paths span the same space. The module may further include a light source and a connector. The connector may be located at the distal end of the optical shaft. The connector may include at least one guide component to position the distal end of the optical shaft adjacent the photodetector of the mobile device. In some embodiments, when the distal end of the optical shaft is positioned adjacent the photodetector of the mobile device, the plurality of first optical components direct the light from the light source to the proximal end of the optical shaft along the first optical path And the plurality of second optical components are configured to direct light along a second optical path from the distal end of the optical shaft to the optical detector of the mobile device.

In some embodiments, the plurality of second optical components comprises a microlens array.

In some embodiments, the optical shaft has a tubular shape.

In some embodiments, the connector includes a plate having a proximal surface and a distal surface, the optical shaft being a continuous extension extending proximal from the proximal surface of the plate. The distal end of the optical shaft forms an opening through the plate.

In some embodiments, at least one guide component is disposed along the periphery of the plate.

In some embodiments, the distal surface of the plate abuts at least a portion of the surface of the mobile device when the distal end of the optical shaft is positioned adjacent the photodetector of the mobile device.

In some embodiments, the at least one guide component is a slot for receiving a mobile device.

In some implementations, the at least one guide component is configured to snap onto a portion of the mobile device.

In some implementations, the at least one guide component is configured to removably attach the module to the mobile device.

In some embodiments, the light source is housed within the optical shaft.

In some embodiments, the light source is a laser.

In some embodiments, the module further comprises a receiving port for mounting the light source to the module, wherein the light shaft is configured to direct light from the light source when the light source is at the receiving port.

In some embodiments, the module further comprises a battery port for receiving the battery. The battery port may be configured to electrically connect the battery to the light source when the battery is in the battery port.

In some implementations, the light source of the module is configured to generate light in response to a signal received from the mobile device.

In another aspect, a method for measuring aberration of a patient's eye includes positioning a module adjacent a mobile device such that the distal end of the optical shaft of the module is adjacent to a photodetector of the mobile device. The method further includes positioning the module adjacent the patient ' s eye such that the proximal end of the optical shaft is adjacent to the patient ' s eye. The method further includes directing light from the light source of the module through the optical shaft and toward the patient ' s eye. The method further includes directing light reflected from the patient's eye to the optical detector of the mobile device via the optical shaft.

In some implementations, positioning the distal end of the optical shaft adjacent the photodetector of the mobile device includes removably attaching the module to the mobile device.

In some embodiments, the method further comprises processing data generated in response to directing light reflected from the patient's eye to a photodetector of the mobile device via the optical shaft.

In some embodiments, the step of processing data comprises measuring a patient's retinal aberration.

In some implementations, processing the data includes processing the data using an application implemented on the mobile device.

In some implementations, the method further includes forwarding the data to a separate device and processing the data using a separate device.

The following description and drawings referred to in this application are not intended to limit the scope, but rather to illustrate an embodiment of the subject matter of the present application. Those skilled in the art will recognize that other implementations of the disclosed method are possible. All such implementations should be considered within the scope of the claims. Each reference number consists of three digits. The first digit corresponds to the reference number for which the reference number is first shown. Reference numerals are not necessarily discussed in the order of their appearances in the drawings.

Figure 1 illustrates a simple overview of an embodiment of an embodiment in which light is reflected from the retina 102 of the patient's eye 101, This light 103 is separated into an array of light spots by the microlens array 104 and is focused by the microlens array to the two-dimensional light detector 105. [ As shown in this example, the two dimensional photodetector may be a camera of a mobile device, such as a smart phone. It should be understood that the combination of a module and a smartphone in this embodiment should not limit the claim to the use of a smartphone, since any mobile device may be used with the module as disclosed in this application.

Figures 2 and 3 are schematic of the optical components in the module and show the path of light from the start of the light up to the time of receipt by the two-dimensional photodetector 220, e.g., the photodetector 105 of Figure 1. [

In certain embodiments, the light source 213 of the module, e.g., a laser, is turned on momentarily. In certain embodiments, light may pass through the aperture stop 209 to reduce the radius of the light beam. The optical path is directed by reflectors 210 and 205 and can be selectively focused as needed by passing through lenses 314 and 316, as shown in FIG. In certain embodiments, one or more of the reflectors 205, 210 may be omitted and the light source 213 may be disposed in a position suitable for directing the light beam towards the beam splitter 206. [

The light source 213 may be of sufficiently low power that the sustained exposure does not damage the patient's eye. This allows the user to turn on the light source 213 early in the measurement and leave the light source on while one or more measurements are obtained. Alternatively, the module may include a switch that may toggle power to the light source 213 in response to a signal transmitted from a mobile device, e.g., Bluetooth, or a similar type of signal, or may be triggered by ignition of the flash of the mobile device . In certain embodiments, the shutter can be used to block light from the light source 213 until a measurement is obtained. Power to the light source 213 may be supplied by a battery reversibly connected to the module, or power may be obtained from the mobile device.

The light beam from light source 213 is directed first toward the light beam along the first optical path using reflector 210 and then by the reflector 205 towards beam splitter 206 Of the eyes. The optional lenses 314 and 316, the reflectors 205 and 210, the aperture stop 209, the beam splitter 206 and the light source 213 are collectively referred to as an "optical component & Which forms the first optical path 211 for the light beam to travel from the light source 213 to the patient ' s retina 201. [ The plurality of optical components is not limited to those shown and may include additional lenses, beam splitters, reflectors, and apertures as desired.

The reflection and transmission ratio of the beam splitter 206 can be selected such that a sufficient amount of light can be transmitted to the eye. Techniques are known in the art for varying the amount of light by varying the reflection and transmission ratio of a beam splitter and for determining the sufficiency of light transmitted by the eye.

After the beam splitter 206, the collimated light is directed to the patient ' s eye, enters the pupil 204 in the eye, and is focused towards the retina 201 by the cornea 202 and lens 203. The collimated light is reflected from the retina 201 and passes through the lens 203 and the cornea 202 again by exiting the pupil 204. Thus, retinal-after-light passes through beam splitter 206 along optical path 212 and then through microlens array 214, e.g., microlens array 104 of FIG. The microlens array 214 includes a plurality of lenses that split and convert light into a two-dimensional array ("spot array") of spots that are individually focused at the focal plane of the microlens array 214. The resulting resulting spot array then passes through lens 207 and lens 208. These lenses 207 and 208 create a conjugate image plane of the spot array toward the photodetector 220. In certain embodiments, the photodetector is a complementary metal-oxide-semiconductor (CMOS) or charge-coupled device (CCD). In certain embodiments, lens 208 and photodetector 220 are components of a mobile device. The lens 208 may be a camera lens of an associated mobile device and may also include a series of lenses.

The lenses 207 and 208, the microlens array 214 and the beam splitter 206 may also collectively be referred to as an " optical component "or a" plurality of second optical components " To the photodetector 220 from the retina of the photodetector. It should be appreciated by one of ordinary skill in the art that at least some of the first and second optical paths span the same space. The term "spanning the same space" means that at least two formed volumes can occupy the same space. For example, two paths whose paths are substantially parallel and overlap are said to span the same space.

As the number of lenses in the microlens array increases, the accuracy of the aberration system increases, but the number of lenses that increase can reduce the dynamic range of the apparatus (the amplitude of optical aberration). The lower dynamic range prevents the aberration system from measuring large aberrations. The number of the aberration lenses can be further limited by the size of each microlens and the size of the light beam entering the microlens array. In certain embodiments, the diameter of the light beam entering the microlens array 214 is between about 2 and about 5 millimeters, corresponding to the size of the patient ' s unexpanded pupil 204, and the microlens array 214 ) May comprise from 5 to 25 lenses along the X-axis, and from 5 to 25 lenses along the Y-axis. In certain embodiments, the microlens array 214 may include from 5 to 20 lenses along the X-axis, and from 5 to 20 lenses along the Y-axis. In certain embodiments, the number of lenses along the X-axis of the array is equal to the number of lenses along the Y-axis.

An alternative design of the optical components in the module is shown in Fig. Figure 3 is different from Figure 2 by the inclusion of optional lenses 314 and 316. [ Many of the module implementations do not include these components in part to minimize the size of the module, in part to reduce manufacturing costs.

The optical design of Figures 2 and 3 places the microlens array 214 within a few tens of millimeters of the pupil 204 to provide a distance within a Rayleigh range used for near field propagation, Providing a reasonable measure of aberration even if the array is not in the conjugate plane of the pupil. These are described in Bauman, BJ and Eisenbies, SK 2006, "Adaptive Optics System Assembly and Integration", edited by Porter, J. et al., Adaptive Optics for Vision Science: Principles, Practices, Design, and Applications , Wiley-Interscience, 187). An alternative design is to add a pair of lenses between the pupil 204 and the microlens array 214, as described in U.S. Patent No. 6,264,328. The pair of lenses form a conjugate image plane of the pupil towards the microlens array 214 and cause an optical measurement of the optical aberration of the eye by the photodetector 220.

Figure 4 shows an example of a contour map caused by how the light reflected from the patient's retina can be captured by the camera of the mobile device and the conversion of the data. As described, light reflected from the retina is converted into spot arrays 401 and 402 as it passes through the microlens array 410, e.g., any microlens array described herein. If the eye is without aberration (e.g., left eye 411), the resulting spot arrays resulting from being captured by the camera of the mobile device may consist of evenly distributed spots 401. Instead, if the eye has aberrations (e.g., right eye 412), the resulting resulting spot array may have a distorted spot distribution.

The images of the spot array can be mathematically transformed through the use of known algorithms in the relevant art (collectively, "computer") by a computer of the mobile device itself or by a computer capable of obtaining images from the mobile device have. Such a transformation can produce a contour map 403 that represents the aberration of the eye. The spot array can also be converted to an eye prescription that can be used by the computer to create a corrective lens 404 for the patient.

The primary source of light reflected from the patient's eye is the light reflected from the retina, but the secondary source of reflected light is the light that can be reflected from the patient's cornea or lens. Such cornea or lens reflex light ("noise") may be lost during processing by the computer or otherwise minimized through the use of known methods and techniques in the related art.

5 is an illustration of an implementation of a module and associated mobile device. In certain embodiments, the optical components of the module are housed within a housing (e.g., a "light shaft"). In certain embodiments, the optical shaft may be tubular (e.g., a "light tube"), such as the optical shaft 501 shown in FIG. The optical shaft 501 has an eye cup 502 at one end (the "patient end" or "proximal end") and at least one opening (503). The device end is in contact with and reversibly connected to the mobile device 504 by a connector. In certain embodiments, the connector includes a back plate 507 having at least one guide component 508 (e.g., a position guide). For example, the guide component 508 may be located along the periphery of the back plate 507. In certain embodiments, at least two or three guide components may be included. As also described, in use, the guide component is reversibly attached to the mobile device such that the photodetector or camera 506 of the mobile device is received within the optical shaft 501 to receive light reflected from the patient's retina To be aligned with the optical components.

In a particular embodiment, the laser light source of the module is also housed within the optical shaft 501, but an alternative design may have a laser outside the optical shaft 501. For example, the laser light source may be adjacent to the optical shaft 501, and the accompanying optical components may direct light from the laser light source into the optical shaft 501. In addition, the optical shaft 501 may also include a user-accessible battery compartment that can maintain the power source of the laser. In certain implementations, the light source of the module may be powered by the mobile device and receive signals from the mobile device (by a physical connection or wireless receiver directly to the mobile device) to generate light. In certain embodiments, the light source is removably attached to the receiving port of the module.

In certain embodiments, the optical shaft 501 may be a continuous extension of the back plate 507 extending proximal from the proximal surface of the back plate 507. The device end 503 of the optical shaft 501 can form an opening through the back plate 507 and allows light reflected from the patient's eye to pass through. The distal surface of the back plate 507 may be in contact with at least a portion of the surface of the mobile device 504. The distal surface of the back plate 507 may be in contact with at least a portion of the surface of the mobile device 504. [ have.

In certain embodiments, the guide component 508 may cause the back plate 507 to snap to the mobile device. In certain embodiments, the back plate 507 may include two guide components 508 that are disposed on opposite sides to allow the back plate 507 to slide toward the mobile device 504. In this embodiment, the third guide component is positioned at the top or bottom edge of the rear plate 507 to prevent further sliding to position the optical shaft 501 adjacent the photodetector 506 of the mobile device 504 Can be located. In certain embodiments, the back plate 507 may be omitted entirely. For example, a portion of the optical shaft 501 may be snapped directly onto the mobile device 504. In certain embodiments, the guide component 508 may be a slot wide enough to receive and hold a portion of the mobile device 504, for example, as shown in Figures 6A and 6B. In certain embodiments, the connector for positioning the optical shaft 501 may be an adhesive that causes the optical shaft 501 to stick to the mobile device 504. In this embodiment, the adhesive may be disposed on the distal surface of the back plate 507. In certain embodiments, the connector may be multiple pieces that extend from the distal end of the optical shaft 501 and that are configured to engage and / or wrap around the mobile device 504. In certain embodiments, the connector may include an alignment mark indicating how to position the optical shaft 501 relative to the photodetector 506.

The tubular shape of the optical shaft 501 is only an illustrative example of an optical shaft, and may be any structure that arranges the optical components of the module, such as a closed housing (e.g., as shown in FIG. 6A) It will be appreciated that the enclosed housing, plate, or any suitable combination thereof, may be considered as an optical shaft.

The exact structure and size of the optical components contained within the optical shaft 501 may be determined through the use of techniques and equations known in the art. In certain embodiments, the position of the openings at the device end of the optical component and optical shaft 501 is held in place during manufacture, so that the openings are aligned with the camera ' Correspond to the position of the lens.

In use, the device end of the optical shaft 501 can be reversibly connected to the mobile device, and the patient end of the optical shaft 501 is held against the eye opening of the patient. When the light source of the module is activated, the light from the light source travels to the patient ' s retina as described, and this light is also reflected back to the camera of the mobile device in the manner described. Data captured by the photodetector or camera may be processed by the mobile device (e.g., by an application running on the mobile device) or delivered to another computer for processing. In this way, if the implementation of the software permits, the patient can monitor their own refraction or snellen fraction. Other implementations of the software may transmit data to the medical care provider for diagnostic or monitoring purposes, or may transmit data to the calibration lens provider to provide the patient with a corrective lens. Whereby the wavefront aberration module as described in this application allows the patient to obtain a measure of retinal aberration without the need to move to the ophthalmoscope or optometrist, thereby increasing the likelihood of compliance with the recommended refractive measurements.

Figure 7 is an exemplary process for measuring aberrations in a patient's eye using any of the embodiments disclosed herein. The process 700 begins at step 702. In step 704, the distal end of the optical shaft of the module is positioned adjacent to the photodetector of the mobile device. The optical shaft may correspond to any of the implementations disclosed herein, such as the optical shaft 501 of FIG. 5 or the optical shaft of FIG. 6A. The mobile device may be any type of mobile device described herein, e.g., the mobile device 504 of FIG. In certain embodiments, the optical shaft is removably attached to the mobile device by a connector, e.g., the back plate 507 and guide component 508 of FIG. 5, such that the optical shaft is positioned adjacent to the photodetector of the mobile device .

In step 706, the proximal end of the optical shaft is positioned adjacent to the patient's eye. For example, the proximal end may be placed in contact with the patient's eye or away from the patient to avoid physical contact. The proximal end may be similar to end 502 and may have an eyecup.

In step 708, the light is directed from the light source of the module through the optical shaft and towards the patient's eye. This can be achieved, for example, by using a plurality of first optical components, such as the optional lenses 314 and 316, the aperture stop 209, the reflectors 205 and 210, and the beam splitter 206 of FIGS. 2 and 3 Can be achieved.

In step 710, the light reflected from the patient's eye is directed through the optical shaft to the photodetector of the mobile device. This can be achieved, for example, using a plurality of second optical components, such as the lenses 207, 208, 214, 314, 316, pinhole aperture 315, and beam splitter 206 of FIG. 3 .

In certain implementations, data generated in response to directing the reflected light from the patient's eye to the photodetector may be processed, for example, by the mobile device itself (using a processor of the mobile device) or by a separate device . According to the methods described herein, data processing may include measuring the patient's retinal aberration. In an implementation in which a separate device processes data, the mobile device may be configured to pass data (processed or unprocessed) to a separate device.

The word "exemplary " or" exemplary "is used herein to mean serving as an example, instance, or illustration. Any aspect or design described herein as "exemplary" or "exemplary " is not necessarily to be construed as preferred or advantageous over other aspects or designs. Rather, the use of the word "exemplary" or "exemplary " As used in this application, the term "or" is intended to mean "exclusive" or "rather than" or ". In other words, unless explicitly stated or otherwise clear in the context, "X includes A or B" is intended to mean any natural inclusive form. That is, X comprises A; X comprises B; If X includes both A and B, then any of the above examples satisfies "X includes A or B ". Also, articles as used in this application and the appended claims should be interpreted generally to mean "one or more " in the context of singular forms, unless the context clearly dictates otherwise. Reference throughout this specification to "an embodiment" or "an embodiment" means that a particular feature, structure, or characteristic described in connection with the embodiment is included in at least one embodiment. Accordingly, the appearances of the phrase "embodiment" or "one embodiment" at various positions throughout this specification are not necessarily all referring to the same embodiment.

It is to be understood that the above description is intended to be illustrative, not limiting. Much Other implementations will be apparent to those of ordinary skill in the relevant arts upon reading and understanding the above description. Accordingly, the scope of the disclosure should be determined with reference to the appended claims, along with the full scope of equivalents to which such claims are entitled.

Claims (20)

A module for use with a mobile device for measuring aberrations of a patient's eye, said module comprising:
An optical shaft having a proximal end and a distal end, the optical shaft comprising a plurality of first optical components arranged to direct light along a first optical path from a distal end to a proximal end, At least a portion of the first and second optical paths extending over the same space;
A light source;
A connector located at a distal end of the optical shaft, the connector comprising at least one guide component for positioning a distal end of the optical shaft adjacent a photodetector of the mobile device, When positioned adjacent to the photodetector:
The plurality of first optical components are configured to direct light from the light source to the proximal end of the optical shaft along the first optical path,
Wherein the plurality of second optical components includes a connector configured to direct light along a second optical path from a distal end of the optical shaft to a photodetector of the mobile device. 2. The module of claim 1, wherein the plurality of second optical components comprises a microlens array. 3. Module according to claim 1 or 2, wherein the optical shaft has a tubular shape. 4. A connector according to any one of claims 1 to 3, wherein the connector comprises a plate having a proximal surface and a distal surface, the optical shaft being a continuous extension extending proximal from the proximal surface of the plate, The module forming an opening through the plate. 5. The module of claim 4, wherein at least one guide component is disposed along a periphery of the plate. 5. The module of claim 4, wherein the distal surface of the plate abuts at least a portion of the surface of the mobile device when the distal end of the optical shaft is positioned adjacent the photodetector of the mobile device. 7. The module of claim 6, wherein the at least one guide component is a slot for receiving a mobile device. 7. The module of claim 6, wherein the at least one guide component is configured to snap onto a portion of the mobile device. 9. The module according to any one of claims 1 to 8, wherein the at least one guide component is configured to removably attach the module to the mobile device. 10. The module according to any one of claims 1 to 9, wherein the light source is housed in an optical shaft. 11. Module according to any one of claims 1 to 10, wherein the light source is a laser. 12. A module according to any one of the preceding claims, further comprising a receiving port for mounting a light source on a module, the optical shaft being configured to direct light from a light source when the light source is in the receiving port. 13. The module according to any one of claims 1 to 12, further comprising a battery port for receiving the battery, the battery port being configured to electrically connect the battery to the light source when the battery is in the battery port. 14. The module according to any one of the preceding claims, wherein the light source of the module is configured to generate light in response to a signal received from the mobile device. A method for measuring aberration of a patient's eye, said method comprising:
Positioning the module adjacent the mobile device such that the distal end of the optical shaft of the module is adjacent the optical detector of the mobile device;
Positioning the module adjacent the patient ' s eye such that the proximal end of the optical shaft is adjacent to the patient ' s eye;
Directing light from the light source of the module through the optical shaft and towards the patient ' s eye; And
Directing light reflected from the patient ' s eye to a photodetector of the mobile device through the optical shaft. 16. The method of claim 15, wherein locating the distal end of the optical shaft proximate the photodetector of the mobile device comprises removably attaching the module to the mobile device. 17. The method of claim 15 or 16, further comprising processing data generated in response to directing light reflected from a patient's eye to a photodetector of the mobile device via the optical shaft. 18. The method of claim 17, wherein the step of processing data comprises measuring a patient's retinal aberration. 18. The method of claim 17, wherein processing data comprises processing data using an application implemented in a mobile device. 18. The method of claim 17, further comprising transmitting data to a separate device, wherein processing data comprises processing data using a separate device.

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