RU2677528C2 - Portable wavefront aberrometer - Google Patents

Abstract

FIELD: medicine.

SUBSTANCE: group of inventions relates to medicine. Module for forming, when used in conjunction with a mobile computing device, a portable wavefront aberrometer for measuring aberrations on a patient's retina includes: a light tube having a proximal and a distal end and comprising a first group of optical components for transmitting light along a first light path from the distal end to the proximal end, and a second group of optical components for transmitting light along the second light path from the proximal end to the distal end, the second group of optical components comprising a microlens array; a light source comprising a laser; and a connector located at the distal end of the light tube, having at least one guiding component for locating the distal end of the light tube near the photodetector of the mobile computing device. When the distal end of the light tube is adjacent to the photodetector of the mobile computing device: the first group of optical components is configured to transmit light from a light source along the first light path to the proximal end of the light tube, and the second group of optical components is arranged to transmit light along the second light path from the distal end of the light tube to the photodetector of the mobile computing device, wherein the second group of optical components is configured to form an array of spots on the photodetector as a result of the passage of light through the microlens array. Method is disclosed for directing light to a photodetector of a mobile computing device for measuring retinal aberrations of a patient, comprising: installing the module adjacent to the mobile computing device so that the distal end of the light tube of the module is adjacent to the photodetector of the mobile computing device; arranging the module near the patient's eye so that the proximal end of the light tube is located adjacent to the patient's eye; directing light from the light source of the module through the light tube to the patient's eye; and directing the light reflected from the patient's eye through the light tube into the photodetector of the mobile computing device, wherein light reflected from the patient's eye passes through the microlens array, leading to the formation of an array of spots on the photodetector.

EFFECT: use of this group of inventions will reduce the size and complexity of the design of the optical system necessary to perform wavefront aberrometry.

17 cl, 7 dwg

Description

Link to a related application

This application claims the priority of provisional patent application US No. 61/922337, filed December 31, 2013

Technical field

The present invention relates to optical devices for detecting and measuring refractive errors of an eye of a patient.

State of the art

In the United States, eyesight testing for children under 6 years of age is usually not performed, exposing it to only 14% of children in this age group. In addition, more than 500 million people worldwide suffer from diseases due to refractive errors, with over 90% of them living in developing countries. Without early diagnosis and correction, this situation is likely to worsen over time.

Both early diagnosis and diagnosis in general can be hindered by a number of factors. One such factor is the problem of communication, which may occur in the case of a small child who is not able to clearly indicate his / her illness, or in a developing country where the patient may not be able to communicate effectively with the healthcare provider. Another factor is costs, which can be a serious obstacle in developing countries, where the cost of equipment for diagnosing refractive errors can be high, and qualified personnel for equipment maintenance and analysis of the results may be absent or difficult to access.

Brief Description of the Drawings

The present invention is illustrated by the attached drawings of specific examples of execution, not limiting the invention. In the drawings, where the same reference numbers denote the same elements, represented:

in FIG. 1 shows the eye, the wavefront created by the light reflected from the retina of the eye, and the matrix of lenses focusing this light on the photodetector of the camera of the mobile device;

in FIG. 2 is a diagram of a wavefront aberrometer in accordance with the invention;

in FIG. 3 shows an alternative wavefront aberrometer scheme in accordance with the invention;

in FIG. Figure 4 shows the differences between the Shack-Hartmann spots corresponding to the normal eye and the eye with refractive errors, and the wavefront contour shapes representing defocus and astigmatism;

in FIG. 5 shows an embodiment of a module and a mobile device associated with it;

in FIG. 6A is a view illustrating an embodiment of a module when using it;

in FIG. 6B is another view illustrating an embodiment of a module when using it; and

in FIG. 7 is a flowchart illustrating a process for measuring aberration of a patient’s eye using any of the disclosed embodiments.

Detailed Description of the Invention

The subject of the present invention relates to the diagnostic equipment most commonly used by ophthalmologists and eyeglass specialists to detect and measure refractive errors of a patient’s eye. In particular, an object of the present invention relates to modules that can be detachably connected to a portable computing device, such as a smartphone, to produce an effective wavefront aberrometer. The present invention uses a light source, for example, a laser on the module, to generate light that must be reflected from the eye. In addition, the disclosed device uses the camera of a portable computing device to receive this reflected light, which can then be converted using software installed on the portable computing device and provided for use by medical professionals and others.

One object of the present invention is to provide a module which, when connected, with the possibility of disconnection, from a portable computing device, such as a smartphone, forms an active wavefront aberrometer. Another objective is to create a cheaper wavefront aberrometer through the use of a portable computing device, which is likely already available to the consumer. Another task is to create a cheaper wavefront aberrometer module, which can be certified by a specialist optician and temporarily transferred to the patient for use in obtaining several data arrays reflecting changes in the patient’s refractive errors. Another objective is the creation of a cheaper wavefront aberrometer module, which can be certified by an optician and given to the patient for a while to obtain refraction measurements, without having to visit an optician, and, in particular, to transfer these measurements to a specialist - optics for the purpose of diagnosis or examination, or the manufacture or otherwise preparation of corrective lenses for purchase. By using the construction principle of the embodiment disclosed herein, it is possible to reduce the costs associated with the wavefront aberrometer, making it suitable for home use or use in areas with limited medical infrastructure, for example, in developing countries.

These problems can be solved by a wavefront aberrometer module (“module”), which can be connected, with the possibility of disconnection, to a mobile computing device (“mobile device”), for example, a smartphone, electronic secretary, compact portable computer or handheld computer. Smartphones are mobile phones having, inter alia, a computer, a luminous screen, and a camera. In accordance with the object of this application can be used and other mobile devices with a camera. For example, mobile devices that can be used in accordance with the disclosed embodiments may be telephones (or smartphones) equipped with a camera, although other devices, such as tablet computers, compact laptop computers, some audio or video players, can also be used. , book readers, each of which can have a photodetector (for example, a camera) and either a central processor or a transceiver for exchanging information received by the camera with another device having a center ln processor. The module may have a guide device for installing or attaching the module to a mobile device, for forming a path of the beam along which the light from the light source can be directed to the patient’s eye, and a path of the beam along which the light from the light source reflected from the patient’s eye, passes through the matrix of microlenses and enters the photodetector.

In the present invention, certain components of the wavefront aberrometer are divided into two components that can be connected to form a working device. One component, a module, includes a system that focuses and directs light into the patient’s eye, and a system that directs light reflected from the patient’s eye through a lens array to a photodetector including a portion of the mobile device. Such a separation provides the main advantage of the object of this application, which consists in sharing the cost and complexity of the wavefront aberrometer between two parts - the module and the mobile device, and the consumer represented part is most likely already available to it or accessible to it.

In use, the module can be attached, with the possibility of detachment, to the mobile device, and fixed in position when the light beam is focused by the module on the eye of the person wearing the aberrometer. When the module is installed in the required position, the light source of the module is activated, and this light is reflected from the retina of the person who put on the aberrometer, passes through the microlens matrix, and finally is received by the camera of the mobile device. The data obtained by the camera can then be processed using algorithms known in the art in the microcomputer of a mobile device, or can be transferred by a mobile device for processing to another computer. The data can be presented to the end user in raw form, or can be presented in processed form, for example, in the form of a recipe for glasses or Snellen fractions. Information provided to the end user may be limited to software installed on the mobile device, and raw or processed data may be sent to the optician for diagnosis and / or preparation of corrective lenses.

Some embodiments of the invention relate to a module for use with a mobile device for measuring aberrations of the eye of a patient. According to one aspect, the module includes a light tube having a proximal end and a distal end. The light tube may include a first group of optical components located so as to direct light along the first light path from the distal end to the proximal end, and a second group of optical components located so as to direct light along the second light path from the proximal end to the distal end. In some embodiments, the at least partially first and second light paths are coextensive. The module may also include a light source and a connector. The connector may be located at the distal end of the light tube. The connector may have at least one guide component for mounting the distal end of the light pipe near the photodetector of the modular device. In some embodiments, the first group of optical components is configured to transmit light from the light source along the first light path to the proximal end of the light pipe, and the second group of optical components is configured to transmit light along the second light path from the distal end of the light pipe to the photodetector of the mobile device when the distal end of the light tube is located near the photodetector of the mobile device.

In some embodiments, the second group of optical components includes a microlens array.

In some embodiments, the light tube has a tubular shape.

In some embodiments, the connector includes a plate having a proximal surface and a distal surface, and the light tube is an adjacent nozzle extending in the proximal direction from the proximal surface of the plate. A through hole in the plate is formed at the distal end of the light tube.

In some embodiments, at least one guide component is located around the perimeter 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 light pipe is adjacent to the photodetector of the mobile device.

In some embodiments, the at least one guide component is a groove for inserting a mobile device into it.

In some embodiments, the at least one guide component is adapted to snap into parts of a mobile device.

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

In some embodiments, the light source is located inside the light pipe.

In some embodiments, the light source is a laser.

In some embodiments, the module also includes a connecting hole for mounting the light source on the module, wherein the light tube is configured to transmit light from the light source when the light source is installed in the connecting hole.

In some embodiments, the module also has a slot for accommodating a battery. The battery slot may be configured to electrically connect the battery to a light source when the battery is in the battery slot.

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

According to another aspect, a method is proposed for measuring aberrations of the patient’s eye, in which the module is mounted adjacent to the mobile device so that the distal end of the light tube of the module is adjacent to the photodetector of the mobile device. When implementing the method, the module is further placed near the human eye so that the proximal end of the light tube is adjacent to the patient’s eye. In the implementation of the method, the light is then directed from the light source of the module through the light tube into the patient’s eye. When implementing the method, the light reflected from the patient’s eye is also directed through the light tube to the photodetector of the mobile device.

In some embodiments, when installing the distal end of the light pipe near the photodetector of a mobile device, the module is attached to the mobile device with the possibility of disconnecting it.

In some embodiments, when implementing the method, the data generated by transmitting light reflected from the patient’s eye through the light pipe to the photodetector of the mobile device is also processed.

In some embodiments, when processing data, aberrations (images) are measured on the patient's retina.

In some embodiments, when processing data, an application program installed on a mobile device is used.

In some embodiments, when the method is implemented, data is also transmitted to a separate device and this separate device is used for processing.

The following description and referenced drawings illustrate an embodiment of the present invention and are not intended to limit the scope of the claims. For specialists it should be clear that other embodiments of the method disclosed herein are possible. All of these options for implementation should be considered covered by the scope of the claims of the formula. Each reference designation is a three-digit number. The first digit corresponds to the number of the figure in which the link number first appeared. Reference signs are not always mentioned in the order they appear on the figures.

In FIG. 1 generally illustrates an embodiment in which light represented by a wavefront (103) of light is reflected from a retina (102) of a patient’s eye (101). This light (103) is separated by a matrix of microlenses (104) into a matrix of light spots and focused by a matrix of microlenses on a two-dimensional photodetector (105). As shown in this drawing, the two-dimensional photodetector may be the camera of a mobile device, for example, a smartphone. It should be borne in mind that the combination of a module with a smartphone in this embodiment should not limit the invention to using only a smartphone, since any mobile device can be used with the module disclosed in this application.

In FIG. 2 and 3 schematically show the components inside the module and show the path of light from the point of radiation to reception on a two-dimensional photodetector (220), for example, a photodetector (105) in FIG. one.

In some embodiments, the light source (213) of the module, such as a laser, is turned on for a short time. In some embodiments, light may pass through the aperture diaphragm (209) to reduce the radius of the light beam. The light beam is guided by mirrors (210, 205) and can, in particular, be focused if necessary when passing through the lenses (314, 316), as shown in FIG. 3. In some embodiments, one or more of the mirrors (205, 210) may be omitted, and the light source (213) may be located in a suitable location for sending the light beam to the beam splitter (206).

The light source (213) must have a sufficiently low power so that prolonged irradiation of the patient's eye cannot damage it. This will allow the user to turn on the light source (213) at the beginning of the measurement and leave it on until one or more measurements are performed. Alternatively, the module may have a switch that will turn on the power of the light source (213) in response to a signal sent from a mobile device, for example, via Bluetooth or a similar signal, or it can be triggered by turning on the flash of the mobile device. In some embodiments, a shutter may be used to block light from the light source (213) until measurements are required. Power to the light source (213) can be supplied from a removable battery connected to the module, or power can be obtained from a mobile device.

First, the light beam from the light source (213) is directed to the patient’s eye along the first beam path using a mirror (210) and then a mirror (205) directing the light to the beam splitter (206). Optional lenses (314, 316), mirrors (205, 210), aperture diaphragm (209), beam splitter (206) and light source (213) together can be called “optical components” or “first group of optical components” forming the first the light path (211) for passing the light beam from the light source (213) to the patient's retina (201). This group of optical components is not limited to those shown in the drawings, and optional lenses, beam splitters, mirrors, and aperture diaphragms can be introduced.

The reflection and transmission coefficients of the beam splitter (206) can be selected so that a sufficient amount of light enters the eye. The methods used to determine the sufficiency of the amount of light directed to the eye and to change this amount by changing the reflection and transmission coefficients of the beam splitter are known in the art.

After passing through the beam splitter (206), the collimated beam of light is directed into the patient’s eye, where it enters the pupil (204) and focuses on the retina (201) with the cornea (202) and the lens (203). The collimated light is reflected from the retina (201) and again passes through the lens (203) and the cornea (202), leaving the pupil (204). Thus, light leaving the retina passes through the beam splitter (206) along the light path (212) and then through the microlens matrix (214), for example, the microlens matrix (104) in FIG. 1. The matrix (214) of microlenses includes a large number of lenses that split and transform light into a two-dimensional matrix of individual focused spots (“spot matrix”) in the focal plane of the matrix (214) of microlenses. The resulting spot matrix is then passed through the lens (207) and the lens (208). These lenses (207, 208) form the conjugate image plane on the photodetector (220). In some embodiments, the photodetector is either a complementary MIS structure (CMOS - from the English. Complementary metal-oxide semiconductor), or a charge-coupled device (CCD - from the English. Charge-coupled device). In some embodiments, the lens (208) and the photodetector (220) are components of a mobile device. The lens (208) may be the camera lens of an attached mobile device, and it may also include multiple lenses.

Lenses (207, 208), microlenses (214), and a beam splitter (206) can also be collectively called “optical components,” or “a second group of optical components,” which forms the second light path through which the light beam passes from the patient’s retina to photodetector (220). Those skilled in the art will appreciate that at least portions of the first and second light paths are “coextensive”. The term "coextensive" means that at least two specific volumes can occupy one space. For example, two paths are called coextensive if they are mostly parallel and overlap.

Although the accuracy of the aberrometer increases as the number of lenses in the microlens array increases, increasing the number of lenses can reduce the dynamic range (amplitude of optical aberrations) of the device. A lower dynamic range may prevent the aberrometer from measuring large aberrations. The number of aberrometer lenses can also be limited by the size of each microlens and the size of the light beam entering the microlens array. In some embodiments, the diameter of the light beam entering the microlens matrix (214) is about 2 to 5 mm, in accordance with the size of the unexpanded pupil (204) of the patient, and the matrix (214) can have 5 to 25 lenses along the axis X and 5 to 25 lenses along the Y axis. In some embodiments, the microlens matrix (214) may have 5 to 20 lenses along the X axis and 5 to 20 lenses along the Y axis. In some embodiments, the number of lenses along the axis X of the matrix is equal to the number of lenses along the Y axis of the matrix.

An alternative arrangement of the optical components in the module is shown in FIG. 3. FIG. 3 differs from FIG. 2 by the inclusion of additional lenses (314, 316). Many embodiments of the module do not include these components, in part, to reduce production costs, as well as to reduce the size of the module.

In the optical circuits shown in FIG. 2 and 3, the microlens matrix (214) is located at a distance of tens of millimeters from the pupil (204) that falls into the Rayleigh scattering region used in the near wave propagation zone, which ensures acceptable accuracy of aberration measurements even when the microlens matrix is not in the conjugate plane of the pupil. This is shown in the article "Adaptive Optics System Assembly and Integration", Bauman, BJ, & Eisenbies, SK, in Adaptive Optics for Vision Science: Principles, Practices, Design, and Applications, Porter J. et al (Ed), Wiley- Intersines, pp. 155-187, 2006. In an alternative scheme, two lenses are added between the pupil (204) and the microlens matrix (214), as described in US Pat. No. 6,264,328. This pair of lenses forms a conjugate image plane of the pupil on the microlens matrix (214), providing the accuracy of measuring optical eye aberrations with a photodetector (220).

In FIG. Figure 4 shows how light reflected from the patient’s retina can be intercepted by the camera of a mobile device, as well as examples of contour diagrams obtained during data conversion. As was shown, the light reflected from the retina is converted into a matrix of spots (401, 402) when passing through a matrix of microlenses (410), for example, the matrix of microlenses described above. If the eye is free from aberrations (for example, the left eye (411)), the resulting matrix of spots, perceived by the camera of the mobile device, may consist of uniformly distributed spots (401). If, on the contrary, the eye has aberrations (for example, the right eye (412)), the resulting matrix of spots received by the camera will have a distorted distribution of spots.

The image of the stain matrix can be mathematically converted using known algorithms by a computer on the mobile device itself, or by a computer that can receive an image from a mobile device (generically, “computer”). One such transformation may be intended to create contour diagrams representing aberrations of the eye (403). The stain matrices can be converted by a computer into an ophthalmologist's prescription, which can be used to make corrective lenses (404) for the patient.

Although the main source of light reflected from the patient’s eye is light reflected from the retina, the secondary source of reflected light is light reflected from the cornea or lens. This corneal or crystalline reflected light (“noise”) can be subtracted during processing by a computer, or can be minimized using methods and techniques known in the relevant field of technology.

In FIG. 5 illustrates an embodiment of a module and associated mobile device. In some embodiments, the optical components of the module are contained in a housing (ie, a light tube). In some embodiments, the light tube may have a tubular shape (for example, a “light tube”), for example, the light tube (501) shown in FIG. 5. The light tube (501) has an eyecup at one end (“user end” or “proximal end”) (502), and at least one hole at the other end (“instrument end” or “distal end”) (503) . The instrument end abuts and connects via a connector, with the possibility of disconnection, with the mobile device (504). In some embodiments, the connector includes a support plate (507) having at least one guide component (508) (e.g., a position lock). For example, the guide component (508) may be located along the perimeter of the support plate (507). In some embodiments, at least two or three guide components may be used. During use, the guide components are detachably attached to the mobile device so that the photodetector or camera (506) of the mobile device is mounted on the same axis as the optical components inside the light tube (501) to receive light reflected from the patient’s retina as described above.

In some embodiments, the laser light source of the module is also located inside the light pipe (501), although in alternative designs the laser can be placed outside the light pipe (501). For example, a laser light source may be adjacent to the light tube (501), and corresponding optical components may direct light from the laser light source to the light tube (501). In addition, the light tube (501) may also include a battery compartment, which can accommodate a laser power source, and which is accessible to the user. In some embodiments, the light source of the module may be powered by a mobile device, or it may receive a signal to generate light (either through a direct physical connection to a mobile device, or wirelessly) from a mobile device. In some embodiments, the light source is installed, with the possibility of disconnection, in the connecting hole of the module.

In some embodiments, the light tube (501) may be an adjacent nozzle to the support plate (507) extending in the proximal direction from the proximal surface of the support plate (507). The instrument end (503) of the light pipe (501) may form an opening in the support plate (507) through which light reflected from the patient’s eye can pass. In some embodiments, the distal surface of the support plate (507) may abut against at least a portion of the surface of the mobile device (504) when the distal end of the light tube (501) is located in close proximity to the photodetector of the mobile device (504).

In some embodiments, the guide component (508) may snap into place with the snap plate (507) to the mobile device. In some embodiments, the support plate (507) may include two guide components (508) located on opposite sides, which allow the support plate (507) to be pushed onto the mobile device (504). In such embodiments, a third guide component may be located on the upper or lower edges of the support plate (507) to prevent further movement, allowing the light tube (501) to be installed near the photodetector (506) of the mobile device (504). In some embodiments, the support plate (507) may not be used at all. For example, a portion of the light tube (501) can be latched directly onto the mobile device (504). In some embodiments, the guide component (508) may be a groove wide enough to insert and hold a portion of the mobile device (504) into it, for example, as shown in FIG. 6A and 6B. In some embodiments, the connector that secures the light pipe (501) may be an adhesive material that adheres the light pipe (501) to the mobile device (504). In such embodiments, the adhesive material may be located on the distal surface of the backing plate (507). In some embodiments, the connector may be composed of several parts extending from the distal end of the light pipe (501) and configured to grab the mobile device (504) and / or wrap around it. In some embodiments, the connector may have alignment marks showing how to mount the light pipe (501) relative to the photodetector (506).

It should be understood that the tubular shape of the light tube (501) is just a particular example to illustrate the light tube, and any structure that can accommodate the optical components of the module, for example, a closed housing, a partially closed housing (for example, shown in FIG. 6A), a plate, or any suitable combination thereof.

The exact relative position and dimensions of the optical components placed inside the light tube (501) can be determined using well-known equations and techniques. In some embodiments, the location of the optical components and the holes on the instrument end of the light pipe (501) is fixed during manufacture so that the hole corresponds to the location of the camera lens of the mobile device, and the light path of the output, or reflected, beam is aligned along the optical axis with the camera’s lens devices.

For use, the instrument end of the light tube (501) can be detachably connected to the mobile device, and the user end of the light tube (501) is pressed against the orbit of the patient. When the module’s light source is turned on, light from the light source passes to the patient’s retina and is reflected toward the camera’s side of the mobile device, as described above. The data received by the photodetector or camera is either processed in a mobile device (for example, using a program installed on the mobile device), or transmitted for processing to another computer. At the same time, the patient has the opportunity, if the installed version of the software allows, to observe the refraction of his eye or Snellen's fraction. Other software options may convert data for a healthcare professional for diagnostic and surveillance purposes, or may convert data for a corrective lens manufacturer to prepare corrective lenses for a patient. Thus, the wavefront aberrometer module described in this application allows the patient to perform aberration measurements on the retina without having to visit an ophthalmologist’s office or optometry, with better compliance with the recommended requirements for refraction measurements.

In FIG. 7 is an illustration of a process for measuring aberrations of a patient’s eye using any of the embodiments disclosed herein. The process (700) begins at step (702). At step (704), the distal end of the light tube of the module is located so that it adjoins the photodetector of the mobile device. The light tube may correspond to any disclosed embodiment, for example the light tube (501) in FIG. 5, or the light tube of FIG. 6A. The mobile device may be a mobile device of any type described herein, for example, the mobile device (504) shown in FIG. 5. In some embodiments, the light tube can be placed near the photodetector of the mobile device by releasably attaching the light tube to the mobile device with a connector, for example, a support plate (507) and a guide component (508) shown in FIG. 5.

At step (706), the proximal end of the light tube is positioned near the patient's eye. For example, the proximal end may abut against the patient’s eye, or may be placed at some distance so that there is no physical contact with the patient. The proximal end may be similar to the end (502) and may include an eyecup.

At step (708), light from the light source of the module is directed through the light tube to the patient’s eye. This can be accomplished, for example, using the first group of optical components, for example optical lenses (314, 316), an aperture diaphragm (209), mirrors (205, 210) and a beam splitter (206) shown in FIG. 2 and 3.

At step (710), the light reflected from the patient’s eye is directed through the light pipe to the photodetector of the mobile device. This can be accomplished, for example, by means of a second group of optical components, for example, lenses (207, 208, 214, 314, 316), aperture diaphragm (315) and beam splitter (206) shown in FIG. 3.

In some embodiments, the data generated by applying light reflected from the patient’s eye to the photodetector can be processed, for example, in the mobile device itself (using the processor of the mobile device) or in a separate device. Data processing may include measuring retinal aberration in accordance with the methods described herein. In embodiments in which data is processed by a separate device, the mobile device may be configured to transmit data (both processed and not processed) to a separate device.

Used in the present description, the words "example" or "illustrative" mean an example, a special case or illustrations. Any features or constructions described herein as an “example” or “illustration” need not be construed as preferred or taking precedence over other features or constructions. On the contrary, the use of the words “example” or “illustrative” implies a statement of principles by concrete examples. In the present application, the term "or" is more likely to include an "or" rather than an exclusive "or". In other words, unless otherwise indicated or clear from the context, “X includes A or B” shall mean any of the usual permutations included. That is, if X includes A; X includes B; or X includes both A and B, then the expression “X includes A or B” is satisfied with any of the above examples. In addition, the indefinite articles used in this application and the attached formula should usually be construed as “one or more” unless otherwise indicated or it is clear from the context that they indicate the singular. References throughout the description to “an embodiment” or “one embodiment” mean that a particular feature, structure, or characteristic described in connection with an embodiment is included in at least one embodiment. Thus, the expressions “embodiment” or “one embodiment” appearing at various places in the present description are not necessarily all referring to the same embodiment.

It should be understood that the above description is intended to illustrate the invention without limiting it. Specialists who have read this understanding and understand it will be able to offer many options for implementation. The scope of the invention should therefore be determined with reference to the attached claims, as well as all possible legal equivalents thereof.

Claims (26)

1. A module for forming, when used together with a mobile computing device, a portable wavefront aberrometer for measuring aberrations on the patient’s retina, including: a light tube having a proximal and distal ends and containing a first group of optical components for transmitting light along a first light path from a distal end to a proximal end and a second group of optical components for transmitting light along a second light path from a proximal end to a distal end, the second group of optical components includes a matrix of microlenses; a light source containing a laser; and a connector located at the distal end of the light pipe having at least one guide component for positioning the distal end of the light pipe near the photodetector of the mobile computing device, wherein when the distal end of the light pipe is adjacent to the photodetector of the mobile computing device: the first group of optical components is configured to transmit light from the light source along the first light path to the proximal end of the light pipe, and the second group of optical components is configured to transmit light along the second light path from the distal end of the light pipe to the photodetector of the mobile computing device, the second group of optical components configured to form a matrix of spots on the photodetector as a result of the passage of light through the microlens matrix. 2. The module according to claim 1, in which the light tube has a tubular shape. 3. The module of claim 1, wherein the connector includes a plate having a proximal surface and a distal surface, the light tube is an adjacent nozzle extending proximal from the proximal surface of the plate, and a through hole is formed in the plate at the distal end of the light tube. 4. The module according to claim 3, in which at least one guide component is located around the perimeter of the plate. 5. The module of claim 3, wherein the distal surface of the plate abuts at least a portion of the surface of the mobile computing device when the distal end of the light pipe is adjacent to the photodetector of the mobile computing device. 6. The module of claim 5, wherein the at least one guide component is a groove for introducing a mobile computing device into it. 7. The module of claim 5, wherein the at least one guide component is latched onto parts of a mobile computing device. 8. The module according to claim 1, in which at least one guide component is configured to detachably attach the module to the mobile computing device. 9. The module of claim 1, wherein the light source is placed inside the light pipe. 10. The module according to claim 1, further having a connecting hole for mounting the light source on the module, and the light tube is configured to transmit light from the light source when the light source is installed in the connecting hole. 11. The module of claim 1, further comprising a battery receptacle configured to electrically connect the battery to a light source when the battery is in the battery receptacle. 12. The module of claim 1, wherein the light source of the module is configured to generate light by a signal received from a mobile computing device. 13. A method of directing light to the photodetector of a mobile computing device for measuring retinal aberrations of a patient’s eye, in which: install the module adjacent to the mobile computing device so that the distal end of the light pipe of the module is adjacent to the photodetector of the mobile computing device; place the module near the patient’s eye so that the proximal end of the light tube is adjacent to the patient’s eye; direct light from the light source of the module through the light tube to the patient’s eye; and direct the light reflected from the patient’s eye through the light pipe to the photodetector of the mobile computing device, the light reflected from the patient’s eye passing through the microlens matrix, leading to the formation of the spots matrix on the photodetector. 14. The method according to p. 13, in which, when installing the distal end of the light pipe adjacent to the photodetector of the mobile computing device, the module is attached to the mobile computing device with the possibility of disconnection. 15. The method according to p. 13, in which the data generated by transmitting light reflected from the patient’s eye through the light pipe to the photodetector of a mobile computing device is processed. 16. The method according to p. 15, in which when processing data using an application program installed on a mobile computing device. 17. The method according to p. 15, in which transmit data to a separate computing device and process the data using this separate computing device.

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