JP2017504408A - Portable wavefront aberration measuring instrument - Google Patents

Abstract

A module for use with a mobile device (504) to measure a patient's eye aberration includes an optical shaft (501) having a proximal end (502) and a distal end (503), and a light source (213, 506). ). The optical shaft (501) is arranged to direct light along a first optical path (211) from the light source (213, 506) to the proximal end (502), a first plurality of optical components (205). , 206, 209, 210, 213, 314, 316) and directs light along the second optical path (212) from the proximal end (502) to the photodetector (220, 506) of the mobile device (504). And a second plurality of optical components (206, 207, 208, 214) arranged to. The connector (507) at the distal end (503) includes at least one guide component (508) for positioning the distal end (503) adjacent to the photodetector (220, 506). When the distal end (503) is positioned adjacent to the photodetector (220, 506), the first plurality of optical components (205, 206, 209, 210, 213, 314, 316) Are guided along the first optical path (211), and a second plurality of optical components (206, 207, 208, 214) guide the light along the second optical path (212). [Selection] Figure 5

Description

[Cross-reference to related applications]
This application claims the benefit of priority of US Provisional Patent Application No. 61 / 922,337, filed December 31, 2013.

  The practice of the present disclosure relates to an optical device for detecting and measuring refractive errors in a patient's eye.

  In the United States, routine vision tests are not performed on children under 6 years of age, and only 14% of children under 6 years have undergone vision tests. In addition, over 500 million people worldwide suffer from illness caused by refractive error, and 90% of these people are in developing countries. Such medical conditions are likely to worsen over time if identified early and not corrected.

US Pat. No. 6,264,328

Bauman, B.M. J. et al. , & Eisenbies, S. K. (2006), “Adaptive Optics System Assembly and Integration,” in Porter, J. et al. , Et al (Ed.), Adaptive Optics for Vision Science: Principles, Practices, Design, and Applications, Wiley-Interscience, pp 155-187.

  Several factors prevent early detection and overall detection. One is communication, which applies to small children who cannot clearly communicate that they are experiencing illness or to those in developing countries where patients may not be able to communicate substantially with their health care providers. Conceivable. Another factor is cost, which may be that the equipment for detecting refraction errors can be expensive and that there are no nearby well-trained personnel to operate the equipment and analyze the results or Limited availability, especially in developing countries.

  The present disclosure is illustrated by way of example and not limitation in the figures of the accompanying drawings in which like reference numerals refer to like elements.

FIG. 6 illustrates a wavefront generated by light reflected from the eye, the retina of the eye, and an array of lenses that focus the light onto a photodetector of a mobile device camera. It is a figure which shows the design of the wavefront aberration measuring device to disclose. It is a figure which shows the alternative design of the wavefront aberration measuring device to disclose. It is a figure which illustrates the difference of the Shack-Hartmann spot corresponding to a normal eye and an eye with a refraction error, and the wavefront outline shape showing defocus and astigmatism. FIG. 6 is an illustration of an implementation of a module and associated mobile device. FIG. 5 is a diagram of an example module in use according to implementation. FIG. 4 is another diagram of an exemplary module in use according to implementation. FIG. 6 illustrates an exemplary process for measuring aberrations in a patient's eye using any of the implementations disclosed herein.

  The subject matter of this application relates to diagnostic instruments most commonly used by ophthalmologists and optometrists to detect and measure refractive errors in a patient's eye. More particularly, the subject matter of the present application relates to a module that can be reversibly attached to a portable computing device, such as a smartphone, thereby creating a functional wavefront aberration meter. The subject matter of this application utilizes a light source, such as a laser, on a module to generate light reflected from the patient's eye. In addition, the disclosed device captures this reflected light using a portable computer device camera, which can then be converted by software on the portable computer device, such as a medical professional Provided for use by.

  One of the objects of the present subject matter is to provide a module that creates a functional wavefront aberration meter when reversibly coupled to a portable computing device such as a smartphone. A further object is to provide an inexpensive wavefront aberration meter by utilizing a portable computing device that a consumer already has. Another objective is the low cost that can be trademarked by an optical specialist and loaned to the patient for use to provide the optical specialist with a variety of data sets that record changes in the refractive error of the patient's eye. A wavefront aberration measuring instrument module is provided. Yet another object is to provide an inexpensive wavefront aberrometer, which can be branded by an optical expert and lend it to the patient so that the patient And optionally make refraction measurements and send these measurements to an optical specialist to generate or otherwise prepare corrective lenses for diagnostic or screening purposes or for purchase Enable. The implementation nature disclosed herein reduces the costs associated with wavefront aberrometers and is a device that can be used in homes or in areas with limited medical infrastructure such as developing countries. To.

  These objectives are achieved by a wavefront aberration measuring module ("module") that can be reversibly attached to a mobile computing device ("mobile device") such as a smartphone, personal digital assistant, laptop, or palmtop computer. can do. A smartphone is a mobile phone that has a computer, illuminated screen, and camera along with other features. Other mobile devices with cameras can also be used in accordance with the subject matter of this application. For example, a mobile device that can be used in accordance with the disclosed implementations may be a camera phone (or smartphone), but a photodetector (such as a tablet computer, laptop computer, certain audio or video players, and e-book readers). For example, a camera) and any other device having either a central processing unit or a transceiver for communicating information captured by the camera to other devices having the central processing unit may be used. To provide a beam path for directing light from the light source to the patient's eye and for the light from the light source reflected from the patient's eye to travel through the array of microlenses onto the photodetector. In addition, the module can include a guide for positioning or mounting the module to a mobile device.

  The subject of the present application separates certain components of the wavefront aberrometer into two components that are joined to form a functional unit. One component, a module, is part of a system that focuses light and directs it to the patient's eye, and part of the mobile device that guides light reflected from the patient's eye through the array of lenses and finally to the photodetector. Including systems including This separation is the main subject of the present application, which divides the cost and complexity of the wavefront aberrometer into a module part and a mobile device part, i.e. a mobile device part that the consumer already has or will have available. Enable the benefits.

  In use, the module can be reversibly mounted on the mobile device and can be fixed in a position such that the light beam from the module's light source is focused by the module onto the patient's eye. Once in position, the module's light source is activated, causing this light to bounce off the wearer's retina and finally pass through the microlens array before being detected by the mobile device camera. The data collected by the camera can then be processed by the mobile device's microcomputer through algorithms known in the art, or the data can be sent by the mobile device to a different computer for processing. it can. The data can be presented unprocessed to the end user, or in a post-processed format such as a spectacle prescription or Snellen fractional vision. The software on the mobile device also restricts the information presented to the end user and sends either raw or post-processed data to the optical specialist for diagnosis and / or processing of the corrective lens be able to.

  Certain implementations of the present disclosure are directed to a module for use with a mobile device to measure aberrations in a patient's eye. In one aspect, the module includes an optical shaft having a proximal end and a distal end. The optical shaft has a first plurality of optical components positioned to direct light from a distal end to a proximal end along a first optical path, and proximal light along the second optical path. A second plurality of optical components positioned to guide from the end to the distal end can be included. In some implementations, at least some of the first and second optical paths are coextensive. In addition, the module can include a light source and a connector. The connector can be located at the distal end of the optical shaft. The connector can include at least one guide component for positioning the distal end of the light shaft adjacent to the photodetector of the mobile device. In some implementations, the first plurality of optical components causes the light from the light source to travel along the first optical path when the distal end of the light shaft is positioned adjacent to the photodetector of the mobile device. The second plurality of optical components is configured to direct light to a proximal end of the optical shaft, and directs light along the second optical path from the distal end of the optical shaft to the photodetector of the mobile device. Configured.

  In some implementations, the second plurality of optical components includes a microlens array.

  In some implementations, the light shaft has a tubular shape.

  In some implementations, the connector includes a plate having a proximal surface and a distal surface, and the light shaft is a continuous extension extending proximally from the proximal surface of the plate. The distal end of the optical shaft defines an opening through the plate.

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

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

  In some implementations, 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 implementations, the light source is housed in a light shaft.

  In some implementations, the light source is a laser.

  In some implementations, the module further includes a receiving port for mounting the light source to the module, and the light shaft is configured to direct light from the light source when the light source is in the receiving port.

  In some implementations, the module further includes a battery port that houses the battery. The battery port can 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 of measuring aberrations in a patient's eye includes positioning the module adjacent to the mobile device such that the distal end of the module's optical shaft is adjacent to the photodetector of the mobile device. . The method further includes positioning the module adjacent to 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 light shaft to the patient's eye. The method further includes directing light reflected from the patient's eye through the optical shaft to the photodetector of the mobile device.

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

  In some implementations, the method further includes processing data generated in response to directing light generated from the patient's eye through the light shaft to the photodetector of the mobile device.

  In some implementations, processing the data includes measuring a patient's retinal aberrations.

  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 transmitting data to another device, and processing the data includes processing the data using another device.

  The following description and drawings referred to herein illustrate the implementation of the subject matter of the present application and are not intended to limit the scope of the invention. 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 figure in the figure whose reference number is displayed first. Reference numbers are not necessarily described in the order in which they appear in the figures.

  FIG. 1 illustrates an overview of an embodiment in which the light represented by the wavefront (103) of light is reflected by the retina (102) of the patient's eye (101). The light (103) is separated into an array of light spots by the microlens array (104), and is focused on the two-dimensional photodetector (105) by the microlens array. As displayed in this illustration, the two-dimensional photodetector can be a mobile device camera such as a smartphone. It will be understood that the combination of module and smartphone in this implementation does not limit the scope of the claims to the use of a smartphone, and any device disclosed in this application can be used with the module. To do.

  2 and 3 are schematic views of the optical components of the module, displaying the light path from generation to reception by a two-dimensional photodetector (220) such as the photodetector (105) of FIG. doing.

  In certain implementations, the light source (213) of a module such as a laser is lit short. In certain implementations, light passes through an aperture stop (209) to reduce the radius of the light beam. The optical path is guided by reflectors (210, 205) and can optionally be focused through lenses (314, 316) as required, as shown in FIG. In certain implementations, one or more of the reflectors (205, 210) can be omitted, and the light source (213) directs the light beam to the spectrometer (206) in the appropriate area. Can be guided.

  The light source (213) is sufficiently low power that long-term exposure will not harm the patient's eyes. Thereby, at the start of the measurement, the user can turn on the light source (213) and leave it on as long as one or more measurements are performed. Alternatively, the module includes a switch that switches power to the light source (213) in response to a signal transmitted from the mobile device, such as Bluetooth or an equivalent signal, or due to the flashing of the mobile device's flash. be able to. In certain implementations, a shutter is used to block light from the light source (213) until a measurement is taken. Power to the light source (213) can be supplied from a battery reversibly connected to the module or taken from a mobile device.

  The light beam from the light source (213) is first guided using the reflector (210) along the first optical path and then by the reflector (205) to the spectroscope (206). It is guided to the patient's eye by directing the light beam to the eye. The optical lens (314, 316), the reflector (205, 210), the aperture stop (209), the spectroscope (206), and the light source (213) are the “optical component” or “first plurality of optical components”. And defines a 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 are not limited to those shown here so that additional lenses, spectrometers, reflectors, and apertures can be included as needed.

  The ratio of reflection and transmission of the spectroscope (206) is selected to allow a sufficient amount of light to reach the eye. Techniques that are used to determine if enough light reaches the eye and change the amount of light by changing the ratio of reflection and transmission of the spectrometer are known in the related art.

  After the spectroscope (206), the collimated light is guided to the patient's eye, enters the pupil (204), and is focused on the retina (201) by the cornea (202) and the lens lens (203). The parallel light is reflected by the retina (201) and passes again through the lens (203) and the cornea (202) present in the pupil (204). Accordingly, the light after retina reflection passes through the spectroscope (206) along the optical path (212) and passes through the microlens array (214) such as the microlens array (104) of FIG. The microlens array (214) includes a plurality of lenses that divide the light and convert it into a two-dimensional array of points (“spot arrays”) that are individually focused at the focus plane of the microlens array (214). The resulting spot array then passes through lens (207) and lens (208). These lenses (207, 208) create a conjugate image plane of the spot array on the photodetector (220). In certain implementations, the photodetector is either a metal oxide semiconductor (CMOS) or a charge coupled device (CCD). In certain implementations, the lens (208) and the photodetector (220) are components of the mobile device. The lens (208) may be an associated mobile device camera lens and may include a series of lenses.

  The lenses (207, 208), the microlens array (214), and the spectroscope (206) are collectively referred to as “optical components” or “second plurality of optical components” and the light beam is transmitted from the patient's retina. A second light path is defined for traveling to the detector (220). One skilled in the art will appreciate that at least a portion of the first and second optical paths are coextensive. The term “coextensive” means that at least two defined volumes occupy the same space. For example, two passages are said to be coextensive when the passages are approximately parallel and overlap.

  Increasing the number of lenses in a microlens increases the accuracy of the aberration meter, but increasing the number of lenses may reduce the dynamic range (optical aberration amplitude) of the device. A lower dynamic range may prevent measuring large aberrations. The number of aberration meter lenses is further limited by the size of each microlens and the size of the light beam entering the microlens array. In certain implementations, the diameter of the light beam entering the microlens array (214) is approximately 2 to 5 millimeters corresponding to the size of the patient's non-dilated pupil (204), and the microlens array (214) is , 5 to 25 lenses on the X axis, and 5 to 25 lenses on the Y axis. In certain implementations, the microlens array (214) can include 5 to 20 lenses on the X axis and 5 to 20 lenses on the Y axis. In certain implementations, the number of X-axis lenses is equal to the number of Y-axis lenses.

  An alternative design of optical components within the module is shown in FIG. FIG. 3 differs from FIG. 2 in that it includes optical lenses (314, 316). Many module implementations do not include these components, one to reduce manufacturing costs and one to minimize the size of the module.

  The optical design of FIGS. 2 and 3 positions the microlens array (214) within tens of millimeters of the pupil, which is distanced to the Rayleigh range used for near-field propagation, so that the microlens array can be It is provided to measure a reasonable aberration even if it is not on a conjugate plane. Such a design is described in Bauman, B .; J. et al. , & Eisenbies, S. K. (2006), “Adaptive Optics System Assembly and Integration,” in Porter, J. et al. , Et al (Ed.), Adaptive Optics for Vision Science: Principles, Practices, Design, and Applications, Wiley-Interscience, pp 155-187. As described in US Pat. No. 6,264,328, an alternative design is to add a pair of lenses between the pupil (204) and the microlens array (214). The pair of lenses form a conjugate image plane of the pupil in the microlens array (214), resulting in an accurate measurement of the optical aberrations of the eye by the photodetector (220).

  FIG. 4 shows an example of how the light reflected from the patient's retina can be captured by the mobile device camera and the contour map resulting from the conversion of the data. As described above, light reflected from the retina passes through a microlens array (410), such as any of the microlens arrays described herein, and is converted to a spot array (401, 402). If the eye is not abnormal (eg, left eye (411)), the resulting spot array captured by the mobile device camera can be composed of uniformly distributed points. Alternatively, if the eye is abnormal (eg, right eye (412)), the resulting captured spot array may have a distorted point distribution.

  The image of the spot array is mathematically transformed using algorithms known in the art by a computer on the mobile device itself or a computer capable of obtaining an image from the mobile device (collectively “computer”). can do. One such transformation can be for creating a contour plot (403) representing the aberrations of the eye. The spot array can be converted by a computer into an ophthalmic prescription that can be used to make a corrective lens (404) for the patient.

  The primary source of light reflected from the patient's eye is light reflected from the retina, but the secondary source of reflected light may be reflected from the patient's cornea or lens lens. . This corneal or retina reflected light ("noise") can be removed while being processed by the computer or otherwise minimized through the use of methods and techniques known in the relevant art.

  FIG. 5 is an illustration of an implementation of a module and associated mobile device. In certain implementations, the optical components of the module can be housed in a housing (ie, a light shaft). In certain implementations, the light shaft can be tubular (ie, a “light tube”), such as the light shaft (501) shown in FIG. The optical shaft (501) has an eyecup at one end (“patient side” or “proximal end”) (502) and at least one at the other end (“device side” or “distal end”). Includes one opening. The device side contacts the mobile device (504) by the connector and is reversibly attached. In certain implementations, the connector includes a backplate (507) having at least one guide component (508) (eg, a position guide). For example, the guide component (508) can be located along the periphery of the backplate (507). In certain implementations, it can include at least two or three guide components. In use, the guide component is reversibly attached to the mobile device so that the photodetector or camera (506) of the mobile device is aligned with the optical component contained within the light shaft (501), which is also Light reflected from the patient's retina is received as described above.

  In certain implementations, the module's laser light source is also included within the optical shaft (501), although alternative designs could have the laser external to the optical shaft (501). For example, the laser light source can be adjacent to the optical shaft (501), and the attached optical component can direct light from the laser light source to the optical shaft (501). In addition, the light shaft (501) can include a battery compartment that can accommodate a user-accessible laser power source. In certain implementations, the light source of the module can be powered from the mobile device and receive light (either by physical direct communication to the mobile device or by a wireless receiver) to provide light. In certain implementations, the light source is removably attached to the receiving port of the module.

  In certain implementations, the light shaft (501) can be a continuous extension of the backplate (507) that extends proximally from the proximal surface of the backplate (507). The device side (503) of the light shaft (501) defines an opening through the backplate (507) to allow light reflected from the patient's eye to pass through. In certain implementations, when the distal end of the light shaft (501) is positioned adjacent to the photodetector of the mobile device (504), the distal surface of the backplate (507) It can contact | abut at least one part.

  In certain implementations, the guide component (508) can allow the backplate (507) to snap to the mobile device. In certain implementations, the back plate (507) has two guide components (508) placed on opposite sides so that the back plate (507) can slide over the mobile device (504). Can be included. In such an implementation, a third guide component that prevents further sliding in order to position the optical shaft (501) adjacent to the photodetector (506) of the mobile device (504) includes a back plate. (507) can be positioned at the upper end or the lower end. In certain implementations, the backplate (507) can be omitted entirely. For example, a portion of the light shaft (501) can be snapped directly to the mobile device (504). In certain implementations, the guide component (508) may be a slot that is wide enough to receive a portion of the mobile device (504), as shown in FIGS. 6A and 6B. In certain implementations, the connector that positions the optical shaft (501) may be an adhesive that adheres the optical shaft (501) to the mobile device (504). In such an implementation, the adhesive can be placed on the distal surface of the backplate (507). In certain implementations, the connector can include a plurality of portions configured to extend from the distal end of the optical shaft (501) to engage and / or surround the mobile device (504). In certain implementations, the connector can include alignment marks that indicate how to position the optical shaft (501) to the photodetector (506).

  The tubular shape of the optical shaft (501) is merely illustrative and can be a module such as a closed housing, a partially closed housing (eg, as shown in FIG. 6A), a flat plate, or any suitable combination thereof. It should be understood that any structure that positions an optical component can be considered as an optical shaft.

  The exact form and size of the optical components housed in the optical shaft (501) can be determined using equations and techniques known in the art. In certain implementations, the positioning of the optical component and the device side opening of the light shaft (501) is such that the opening is aligned with the mobile device camera lens so that the outward or reflected light path is aligned with the mobile device camera lens. The position is fixed during manufacture to correspond with the position of the lens.

  In use, the device side of the optical shaft (501) is reversibly connected to the mobile device, and the patient side of the optical shaft (501) can be fixed in the direction of the patient's orbit. When the module's light source is activated, light from the light source travels to the patient's retina as disclosed, and this light is reflected back to the mobile device camera in a disclosed manner. Data captured by the photodetector or camera is processed by a mobile device (eg, by an application running on the mobile device) or transmitted to another computer for processing. In this way, the patient can monitor his refraction or Snellen fractional visual acuity if the software implementation allows. In other implementations of the software, data can be sent to a health care provider for diagnosis or monitoring, or data can be sent to a corrective lens provider to provide a corrective lens to a patient. The wavefront aberrometer module described in this application allows a patient to measure retinal aberrations without going to the ophthalmologist or optometry office, thereby encouraging more observance of recommended refraction measurements. .

  FIG. 7 is an exemplary process for measuring aberrations in a patient's eye using any of the implementations disclosed herein. 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 implementation disclosed herein, such as the optical shaft (501) of FIG. 5 or the optical shaft of FIG. 6A. The mobile device can be any type disclosed herein, such as the mobile device (504) of FIG. In certain implementations, the optical shaft is removably attached to the mobile device using connectors such as the backplate (507) and guide component (508) of FIG. Can be positioned adjacent to.

  In step (706), the proximal end of the optical shaft is positioned adjacent to the patient's eye. For example, the proximal end can be abutted against the patient's eye or can be positioned away so as not to physically contact the patient. The proximal end may be similar to end (502) and may have an eyecup.

  In step (708), light is directed from the module's light source through the light shaft toward the patient's eye. This includes, for example, a first plurality of optical components such as the optical lenses (314, 316), aperture stop (209), reflectors (205, 210), and spectrometer (206) of FIGS. Can be achieved by using.

  In step (710), light reflected from the patient's eye is directed through the optical shaft to the photodetector of the mobile device. This can be accomplished, for example, by using second optical components such as the lens (207, 208, 214, 314, 316), pinhole stop (315), and spectrometer of FIG.

  In certain implementations, data generated in response to light reflected from the patient's eye being directed to the photodetector is, for example, by the mobile device itself (using the mobile device's processing components). Or by another device. The data processing step may include measuring a patient's retinal aberrations according to the methods described herein. In an implementation where another device processes the data, the mobile device can be configured to send the data (either processed or unprocessed) to the other device.

  The word “example” or “exemplary” is used herein to mean serving as an example, instance, or illustration. Any aspect or design described herein as "example" or "exemplary" is not necessarily to be construed as preferred or advantageous over other aspects or designs. Rather, use of the word “example” or “exemplary” is intended to present concepts in a concrete fashion. As used in this application, the term “or” is intended to mean an exhaustive “or” rather than an exclusive “or”. That is, unless otherwise apparent from the context or context, “X includes A or B” is intended to mean any natural exhaustive substitution. That is, when X includes A, X includes B, or X includes both A and B, “X includes A or B” is satisfied under all the conditions of the previous example. In addition, the articles “a” and “an” as used in the present application and claims mean “one or more” unless clearly indicated otherwise by the specification or context. Should be interpreted as a whole. Reference to “implementation” or “one implementation” throughout this specification means that the particular feature, structure, or characteristic described in connection with the implementation is included in at least one implementation. Thus, the appearances of the phrases “implementation” or “one implementation” in various places throughout this specification are not necessarily referring to the same implementation.

  It should be understood that the above description is intended to be illustrative rather than limiting. Many other implementations will be apparent to those of skill in the art upon reading and understanding the above description. The scope of the present disclosure should, therefore, be determined with reference to the appended claims, along with the full scope of equivalents to which such claims are entitled.

501 Optical shaft 502 Proximal end 504 Mobile device 507 Back plate 508 Guide component

Claims (20)

A module for use with a mobile device to measure aberrations in a patient's eye,
A first plurality of optical components having a proximal end and a distal end and arranged to guide light from the distal end to the proximal end along a first optical path; A second plurality of optical components positioned to guide along two optical paths from the proximal end to the distal end, wherein at least one of the first and second optical paths A portion of the optical shaft that is coextensive;
A light source;
A connector positioned at the distal end of the optical shaft and including at least one guide component for positioning the distal end of the optical shaft adjacent to a photodetector of the mobile device, the connector comprising: When the distal end of the optical shaft is positioned adjacent to the photodetector of the mobile device;
The first plurality of optical components are configured to direct light from the light source along the first optical path to the proximal end of the optical shaft, and the second plurality of optical components. Is configured to guide light along the second optical path from the distal end of the optical shaft to the photodetector of the mobile device,
The connector;
A module characterized by including.   The module of claim 1, wherein the second plurality of optical components includes a microlens array.   The module according to claim 1, wherein the optical shaft has a tubular shape. The connector includes a plate having a proximal surface and a distal surface;
The optical shaft is a continuous extension extending proximally from the proximal surface of the plate;
The distal end of the optical shaft defines an opening through the plate;
The module according to any one of claims 1 to 3, characterized in that:   The module of claim 4, wherein the at least one guide component is disposed along a circumference of the plate.   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 to the photodetector of the mobile device. The module according to claim 4.   The module of claim 6, wherein the at least one guide component is a slot for receiving the mobile device.   The module of claim 6, wherein the at least one guide component is configured to snap onto a portion of the mobile device.   9. A module according to any preceding claim, wherein the at least one guide component is configured to removably attach the module to the mobile device.   The module according to claim 1, wherein the light source is accommodated in the optical shaft.   The module according to any one of claims 1 to 10, wherein the light source is a laser. An accepting 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 in the accepting port;
The module according to claim 1, further comprising: A battery port for containing a battery, wherein the battery port is configured to electrically connect the battery to the light source when the battery is in the battery port;
The module according to claim 1, further comprising:   14. A 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 aberrations in a patient's eye, comprising:
Positioning the module adjacent to the mobile device such that the distal end of the optical shaft of the module is adjacent to the photodetector of the mobile device;
Positioning the module adjacent to 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 toward the patient's eye;
Directing light reflected from the patient's eye through the optical shaft to the photodetector of the mobile device;
A method comprising the steps of:   16. The method of claim 15, wherein positioning the distal end of the light shaft adjacent to the photodetector of the mobile device includes removably mounting the module to the mobile device. The method described.   16. The method of claim 15, further comprising processing data generated in response to directing the light reflected from the patient's eye through the optical shaft to the photodetector of the mobile device. Or the method of any one of Claim 16.   The method of claim 17, wherein processing the data comprises measuring retinal aberrations of the patient.   The method of claim 17, wherein processing the data comprises processing the data using an application implemented on the mobile device. Further comprising transmitting the data to another device;
Processing the data includes processing the data using the another device;
The method according to claim 17, wherein:

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