JP2019111443A - Portable wavefront aberrometer - Google Patents

Abstract

To provide a module for use with a device for detecting and measuring refractive errors of a patient's eye.SOLUTION: A module for use with a mobile device (504) to measure an aberration of a patient's eye includes a light shaft (501) having a proximal end (502) and a distal end (503), and light sources (213, 506). The light shaft includes a first plurality of optical components arranged to direct light along a first light path from the light source to the proximal end, and a second plurality of optical components arranged to direct light along a second light path from the proximal end to a light detector of the mobile device. A connector at the distal end includes at least one guide component for positioning the distal end adjacent to the light detector. When the distal end is positioned adjacent to the light detector, the first plurality of optical components directs light along the first light path and the second plurality of optical components directs light along the second light path.SELECTED DRAWING: Figure 5

Description

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

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

  In the United States, routine vision testing is not performed on children under 6 years of age, with only 14% of children under 6 years of age receiving visual acuity testing. In addition, more than 500 million people worldwide suffer from diseases caused by refractive errors, and 90% of these people are in developing countries. Such medical conditions are likely to deteriorate over time if they are identified early and not corrected.

U.S. Patent No. 6,264,328

Bauman, B .; J. , & Eisenbies, S. K. (2006), "Adaptive Optics System Assembly and Integration," in Porter, J. Org. , 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 may be the case in small children who can not be clearly informed that they are experiencing an illness or in developing countries where patients may not be able to communicate substantially with the healthcare provider. Conceivable. Another factor is cost, which may be expensive equipment for detecting refractive errors, and there may not be nearby trained personnel to operate the equipment and analyze the results Limited availability, especially in developing countries.

  The disclosure of the present invention is illustrated by way of example and not limitation in the figures of the accompanying drawings in which like references indicate similar elements.

FIG. 2 illustrates an eye, a wavefront generated by light reflected from the retina of the eye, and an array of lenses focusing the light onto a photodetector of a mobile device camera. It is a figure which shows the design of the wavefront aberration measuring instrument to disclose. FIG. 7 shows an alternative design of the disclosed wavefront aberration measurement instrument. FIG. 5 illustrates the difference between Shack-Hartmann spots corresponding to normal and refractive error eyes, and wavefront contour shapes representing defocus and astigmatism. FIG. 5 is an illustration of an implementation of a module and associated mobile device. FIG. 7 is a diagram of an exemplary module in use according to an implementation. FIG. 7 is another view of an exemplary module in use according to an implementation. FIG. 6 illustrates an exemplary process for measuring the aberration of a patient's eye using any of the implementations disclosed herein.

  The subject matter of the present application relates to diagnostic equipment most commonly used by ophthalmologists and optometrists to detect and measure refractive errors of 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 smart phone, thereby making a functional wavefront aberrometer. The subject matter of the present application utilizes a light source, such as a laser, located on the module to generate light reflected from the patient's eye. In addition, the disclosed device captures this reflected light using a portable computing device camera, which can then be converted by software on the portable computing device, such as a medical professional Provided for use by

  One of the objects of the subject matter of the present application is to provide a module that makes a functional wavefront aberrometer when reversibly coupled to a portable computing device such as a smartphone. A further object is to provide an inexpensive wavefront aberrometer by utilizing portable computing devices that consumers are already believed to have. Another object is an inexpensive, loaned to a patient for use as an optical specialist, which can be trademarked by the optical specialist and used to provide the optical specialist with various data sets that record changes in refractive error of the patient's eye. It is an object of the present invention to provide a wavefront aberration measuring instrument module. Yet another object is to provide an inexpensive wavefront aberrometer, which can be branded by an optical specialist, and by lending it to a patient, the patient can be an optical specialist. Sending refractometric measurements to optical specialists to make or otherwise prepare corrective lenses for diagnostic or screening purposes or for purchase, and optionally without visiting Make it possible. The nature of the implementation disclosed herein reduces the costs associated with wavefront aberrometers, and can be implemented in areas where the wavefront aberrometers are for home use or where medical infrastructure is limited, such as in developing countries. Make it

  These goals are achieved by a wavefront aberrometer 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, an illuminated screen, and a camera along with other features. Other mobile devices with cameras can also be used in accordance with the subject matter of the present application. For example, the mobile device that can be used according to the disclosed practice may be a camera phone (or smart phone), but a light detector (such as a tablet computer, laptop computer, specific audio or video player, and electronic book reader For example, all other devices having a camera) and either a central processing unit or a transceiver for transmitting information captured by the camera to other devices with the central processing unit can also be used. To provide a beam path that directs light from the light source to the patient's eye, and to provide a beam path that light from the light source reflected from the patient's eye travels through the array of microlenses onto the light detector In addition, the module can include a guide for positioning or mounting the module on the mobile device.

  The subject matter of the present application separates certain components of the wavefront aberrometer into two components joined together to form a functional unit. One component, the module, is a system that focuses and directs light to the patient's eye, and a part of the mobile device that directs the light reflected from the patient's eye through the array of lenses and finally to the light detector Including systems that This separation is the main part of the subject matter of the present application of dividing the cost and complexity of the wavefront aberration measuring instrument into a modular part and a mobile device part, ie a mobile device part already possessed or obtainable by the consumer mentioned above. Enable the benefits.

  In use, the module can be reversibly attached to 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 light source of the module is activated, causing the light to bounce back to the wearer's retina, and finally 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 transmitted by the mobile device to a different computer for processing it can. The data can be presented to the end user in an unprocessed state or in a processed format, such as a prescription for eyeglasses or Snellen's fractional vision. The software on the mobile device also limits the information shown to the end user and sends either raw or processed data to the optical specialist for diagnosis and / or for processing of corrective lenses be able to.

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

  In some implementations, the second plurality of optical components comprises 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 light 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 light shaft is located adjacent to the light detector of the mobile device.

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

  In some implementations, 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 on 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 at the receiving port.

  In some implementations, the module further includes a battery port that houses a 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 sources of the module are configured to generate light in response to signals received from the mobile device.

  In another aspect, a method of measuring aberration of a patient's eye includes positioning a module adjacent to a mobile device such that a distal end of a light shaft of the module is adjacent to a light detector of the mobile device . The method further includes positioning the module adjacent to the patient's eye such that the proximal end of the light shaft is adjacent to the patient's eye. The method further includes directing the 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 light shaft to a light detector of the mobile device.

  In some implementations, positioning the distal end of the light shaft adjacent to the light detector of the mobile device includes removably attaching 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 light detector of the mobile device.

  In some implementations, processing the data includes measuring aberrations of the patient's retina.

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

  In some implementations, the method further comprises transmitting the data to another device, and processing the data includes processing the data using the other device.

  The following description and drawings referenced 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 3 digits. The first digit corresponds to the figure in which the reference number is first displayed. 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 of light (103) is reflected at the retina (102) of the patient's eye (101). This light (103) is separated into an array of light spots by a microlens array (104) and focused by a microlens array to a two-dimensional photodetector (105). As displayed in this illustration, the two-dimensional light detector can be a mobile device camera such as a smart phone. It is to be understood that the combination of module and smartphone in this implementation does not limit the claims to the use of the smartphone, and any device disclosed in the present application can be used with the module. Do.

  FIGS. 2 and 3 are schematic diagrams of the optical components of the module, showing the path of light from generation to being received by a two-dimensional photodetector (220), such as the photodetector (105) of FIG. doing.

  In certain implementations, the light source (213) of the module, such as a laser, lights up briefly. In certain implementations, light passes through the aperture stop (209) to reduce the radius of the light beam. The light path is guided by reflectors (210, 205) and can optionally be focused through lenses (314, 316) as shown in FIG. In certain implementations, one or more of the reflectors (205, 210) can be omitted and the light source (213) is placed in the appropriate area to direct the light beam to the spectroscope (206) It can be induced.

  The light source (213) is sufficiently low power that prolonged exposure will not damage the patient's eye. Thereby, at the start of the measurement, the user can turn on the light source (213) and leave it on while one or more measurements are taken. Alternatively, the module sends power to the light source (213) in response to signals transmitted from the mobile device, such as Bluetooth or equivalent signal, or due to the lighting of the flash of the mobile device. A switch can be included to switch. In certain implementations, a shutter is used to block light from the light source (213) until a measurement is made. Power to the light source (213) can be supplied from a battery reversibly connected to the module or taken from the mobile device.

  The light beam from the light source (213) first guides the light beam along the first optical path using a reflector (210) and then by means of the reflector (205) a spectroscope (206) The light beam is directed to the patient's eye by directing the light beam. The optical lens (314, 316), the reflector (205, 210), the aperture stop (209), the spectroscope (206), and the light source (213) may be "optical components" or "first plurality of optical components And define a first light 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, as additional lenses, spectroscopes, reflectors, and stops can be included as needed.

  The reflectance and transmission rates of the spectroscope (206) are selected to allow a sufficient amount of light to reach the eye. Techniques used to determine whether the light reaching the eye is sufficient, and changing the rate of reflection and transmission of the spectrometer to change the amount of light, are known in the relevant art.

  After the spectroscope (206), collimated light is directed into 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 collimated light is reflected at the retina (201) and passes again through the lens lens (203) and the cornea (202) present at the pupil (204). Thus, light after retinal 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 multiple lenses that split 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 light detector (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 light detector (220) are components of a 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 Define a second light path for going to the detector (220). Those skilled in the art will appreciate that at least a portion of the first and second light paths are coextensive. The term "co-extensive" means that at least two defined volumes occupy the same space. For example, two passages are said to be coextensive if the passages are approximately parallel and overlapping.

  While increasing the number of lenses in the microlens increases the accuracy of the aberrometer, increasing the number of lenses may reduce the dynamic range of the device (the amplitude of the optical aberration). Lower dynamic range may prevent measuring large aberrations. The number of lenses of the aberrometer 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 about 2 to 5 millimeters, corresponding to the size of the patient's unpopulated 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 in the X axis and 5 to 20 lenses in the Y axis. In certain implementations, the number of lenses in the X axis and the number of lenses in the Y axis are equal.

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

  The optical design of FIGS. 2 and 3 locates the microlens array (214) within a few tens of millimeters of the pupil distanced to the Rayleigh range used for near-field propagation, so that even if the microlens array is the pupil Provide a reasonable measurement of aberrations even if they are not in the conjugate plane. Such a design is described by Bauman, B., et al. J. , & Eisenbies, S. K. (2006), "Adaptive Optics System Assembly and Integration," in Porter, J. Org. Et al (Ed.), Adaptive Optics for Vision Science: Principles, Practices, Design, and Applications, Wiley-Interscience, pp 155-187. An alternative design is to add a pair of lenses between the pupil (204) and the microlens array (214), as described in US Pat. No. 6,264,328. A 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 light detector (220).

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

  The image of the spot array is mathematically transformed using an algorithm known in the art by means of a computer capable of obtaining an image from the mobile device's own computer or from the mobile device (together, "computer"). can do. One such transformation may be to create a contour plot (403) that represents the aberrations of the eye. The spot array can be converted by the computer into an ophthalmic prescription that can be used to make the patient's corrective lens (404).

  The main source of light reflected from the patient's eye is light reflected from the retina, but the source of secondary reflected light may be reflected from the patient's cornea or lens lens . This reflected light ("noise") of the cornea or retina can be removed during processing 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 (i.e., an optical shaft). In certain implementations, the light shaft can be tubular (i.e., a "light tube") such as the light shaft (501) shown in FIG. The light 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") Including two openings. The device side is attached to the mobile device (504) by the connector and attached reversibly. In certain implementations, the connector includes a backplate (507) having at least one guide component (508) (e.g., a position guide). For example, the guide component (508) can be located along the perimeter of the backplate (507). In certain implementations, at least two or three guide components can be included. In use, the guide component is reversibly attached to the mobile device such that the photodetector or camera (506) of the mobile device aligns with the optical component contained within the light shaft (501), also It receives light reflected from the patient's retina as described above.

  In certain implementations, the laser light source of the module is also included in the light shaft (501), but in an alternative design, the laser may be external to the light shaft (501). For example, the laser light source can be adjacent to the light shaft (501) and the attached optical component can direct light from the laser light source to the light shaft (501). In addition to this, the light shaft (501) can include a battery compartment that can accommodate the power of the user accessible laser. In certain implementations, the light sources of the modules can be powered from the mobile device and receive signals (either by direct physical 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. In certain implementations, when the distal end of the light shaft (501) is positioned adjacent to the light detector of the mobile device (504), the distal surface of the backplate (507) is the mobile device (504) Can be in contact with at least part of the

  In certain implementations, the guide component (508) can allow the backplate (507) to be snapped to the mobile device. In certain implementations, the backplate (507) has two guide components (508) placed on opposite sides, so that the backplate (507) can slide on the mobile device (504). Can be included. In such an implementation, to position the light shaft (501) adjacent to the light detector (506) of the mobile device (504), backplate a third guide component to prevent further sliding. It can be positioned at the upper or lower end of (507). In certain implementations, the backplate (507) can be completely omitted. 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) can be a slot 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 light shaft (501) can be an adhesive that bonds the light shaft (501) to the mobile device (504). In such implementations, an adhesive can be placed on the distal surface of the backplate (507). In certain implementations, the connector can include a plurality of portions extending from the distal end of the light 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 light shaft (501) on the light detector (506).

  The tubular shape of the light shaft (501) is merely an illustrative example, and may 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 is to be understood that any structure for positioning an optical component can be considered as an optical shaft.

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

  In use, the device side of the light shaft (501) can be reversibly connected to the mobile device, and the patient side of the light shaft (501) can be fixed in the direction of the patient's orbit. When the module 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 manner also disclosed. Data captured at the light detector or camera may be processed by the mobile device (e.g., by an application running on the mobile device) or transmitted to another computer for processing. In this method, the patient can monitor his refractive or Snellen-type fractional vision if the software implementation permits. In other implementations of the software, data can be sent to the healthcare provider for diagnosis or monitoring, or data can be sent to the provider of the corrective lens to provide the patient with a corrective lens. The wavefront aberrometer module described in the present application allows the patient to measure retinal aberrations without going to the ophthalmology or ophthalmologist, which is expected to be more compliant with the recommended refraction measurements .

  FIG. 7 is an exemplary process of measuring aberration of a patient's eye using any of the implementations disclosed herein. Process (700) begins with step (702). At step (704), the distal end of the light shaft of the module is positioned adjacent to the light detector of the mobile device. The light shaft may correspond to any of the implementations disclosed herein, such as the light shaft (501) of FIG. 5 or the light 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 light shaft can be a photodetector of the mobile device by removably attaching the light shaft to the mobile device using a connector such as the backplate (507) and the guide component (508) of FIG. It can be positioned adjacent to

  At step (706), the proximal end of the light shaft is positioned adjacent to the patient's eye. For example, the proximal end can be abutted against the patient's eye or positioned remotely away from physical contact with the patient. The proximal end may be similar to the end (502) and may have an eye cup.

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

  In step 710, light reflected from the patient's eye is directed through the light shaft to the light detector of the mobile device. This can be achieved, for example, by using a second optical component such as the lens (207, 208, 214, 314, 316) of FIG. 3, a pinhole stop (315), and a spectroscope.

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

  The words "example" or "exemplary" are 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, the use of the words "example" or "exemplary" seeks to present the concept in a concrete form. As used in this application, the term "or" is intended to mean the inclusive "or" rather than the exclusive "or". That is, unless otherwise apparent from the specification or context, "X includes A or B" is intended to mean any natural exhaustive substitution. That is, when X contains A, X contains B, or X contains both A and B, "X contains A or B" is satisfied under all the conditions of the previous example. In addition to this, the articles "a" and "an" as used in the present application and claims mean "one or more than one" unless clearly indicated otherwise by the specification or context of the present application and claims. So it must be interpreted as a whole. References to "implementation" or "one implementation" throughout this specification mean that the specific features, structures or characteristics described in connection with the implementation are included in at least one implementation. Thus, the appearances of the phrase "implement" or "one implementation" at various places throughout the specification are not necessarily all referring to the same implementation.

  It is to be understood that the above description is intended to be illustrative, and not restrictive. Many other implementations will be apparent to one of ordinary 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 light shaft 502 proximal end 504 mobile device 507 backplate 508 guide component

Claims (20)

A module for use with a mobile device to measure aberrations of a patient's eye, comprising:
A first plurality of optical components having a proximal end and a distal end and disposed to direct light along the first optical path from the distal end to the proximal end; An optical shaft including a second plurality of optical components positioned to guide along the two optical paths from the proximal end to the distal end, at least one of the first and second optical paths The light shaft being partially coextensive;
Light source,
A connector comprising at least one guide component located at the distal end of the light shaft and for positioning the distal end of the light shaft adjacent to a light detector of the mobile device, the connector comprising: When the distal end of the light shaft is positioned adjacent to the light detector 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 light shaft, and the second plurality of optical components Is configured to direct light along the second light path from the distal end of the light shaft to the light detector of the mobile device.
Said connector,
A module characterized by including:   The module of claim 1, wherein the second plurality of optical components comprises a microlens array.   The module according to any one of claims 1 or 2, wherein the light shaft has a tubular shape. The connector includes a plate having a proximal surface and a distal surface,
The light shaft is a continuous extension extending proximally from the proximal surface of the plate;
The distal end of the light shaft defines an opening through the plate
The module according to any one of claims 1 to 3, characterized in that:   5. The module of claim 4, wherein the at least one guide component is disposed along the periphery of the plate.   The distal surface of the plate abuts at least a portion of a surface of the mobile device when the distal end of the optical shaft is positioned adjacent to the light detector of the mobile device. The module according to claim 4.   7. 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 of the preceding claims, wherein the at least one guide component is configured to removably attach a module to the mobile device.   The module according to any one of the preceding claims, wherein the light source is housed within the light shaft.   The module according to any one of claims 1 to 10, wherein the light source is a laser. A receiving port for mounting the light source to a module, wherein the light shaft is configured to direct light from the light source when the light source is at the receiving port;
The module according to any one of claims 1 to 11, further comprising: A battery port for containing a battery, the battery port configured to electrically connect the battery to the light source when the battery is at the battery port;
The module according to any one of claims 1 to 12, further comprising:   14. A module according to any of the preceding claims, wherein the light source of a module is configured to generate light in response to a signal received from the mobile device. A method of measuring the aberration of a patient's eye, comprising:
Positioning the module adjacent to the mobile device such that the distal end of the light shaft of the module is adjacent to the light detector of the mobile device;
Positioning the module adjacent to the patient's eye such that the proximal end of the light shaft is adjacent to the patient's eye;
Directing light from a light source of the module through the light shaft and towards the patient's eye;
Directing light reflected from the patient's eye through the light shaft to the light detector of the mobile device;
A method characterized by comprising.   16. The method of claim 15, wherein positioning the distal end of the light shaft adjacent the light detector of the mobile device comprises removably mounting the module to the mobile device. 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 light shaft to the light detector 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 other device.
The method according to claim 17, characterized in that.