WO2020086693A1 - Dispositifs et systèmes de dépistage portables pour diagnostics ophtalmiques à distance - Google Patents

Dispositifs et systèmes de dépistage portables pour diagnostics ophtalmiques à distance Download PDF

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Publication number
WO2020086693A1
WO2020086693A1 PCT/US2019/057618 US2019057618W WO2020086693A1 WO 2020086693 A1 WO2020086693 A1 WO 2020086693A1 US 2019057618 W US2019057618 W US 2019057618W WO 2020086693 A1 WO2020086693 A1 WO 2020086693A1
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WO
WIPO (PCT)
Prior art keywords
eye
patient
slit
facing side
data
Prior art date
Application number
PCT/US2019/057618
Other languages
English (en)
Inventor
Frank TALKE
Gerrit MELLES
Alex PHAN
Phuong TRUONG
Buu TRUONG
Nicolas WILLIAMS
Original Assignee
The Regents Of The University Of California
Melles Research Foundation Usa, Inc.
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Priority claimed from NL2021870A external-priority patent/NL2021870B1/en
Application filed by The Regents Of The University Of California, Melles Research Foundation Usa, Inc. filed Critical The Regents Of The University Of California
Priority to US17/285,946 priority Critical patent/US20210330186A1/en
Priority to AU2019365201A priority patent/AU2019365201A1/en
Priority to EP19875120.8A priority patent/EP3870026A4/fr
Priority to CA3117117A priority patent/CA3117117A1/fr
Publication of WO2020086693A1 publication Critical patent/WO2020086693A1/fr

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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B3/00—Apparatus for testing the eyes; Instruments for examining the eyes
    • A61B3/18—Arrangement of plural eye-testing or -examining apparatus
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B3/00—Apparatus for testing the eyes; Instruments for examining the eyes
    • A61B3/10—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions
    • A61B3/12—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions for looking at the eye fundus, e.g. ophthalmoscopes
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B3/00—Apparatus for testing the eyes; Instruments for examining the eyes
    • A61B3/10—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions
    • A61B3/13—Ophthalmic microscopes
    • A61B3/135—Slit-lamp microscopes
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B3/00—Apparatus for testing the eyes; Instruments for examining the eyes
    • A61B3/10—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions
    • A61B3/16—Objective types, i.e. instruments for examining the eyes independent of the patients' perceptions or reactions for measuring intraocular pressure, e.g. tonometers

Definitions

  • a field of the invention is ophthalmic devices.
  • the invention provides devices and systems for remote ophthalmic screening and diagnostics.
  • Ophthalmic devices permit a professional to conduct eye examinations. State of the art devices are built primarily for office examinations by professionals. Remote medicine holds great potential to reduce costs, improve patient care and shift focus to substantive examination and professional-patient interaction.
  • Preferred embodiments of the invention provide ophthalmic devices that can be used in traditional professional office settings or can be used for the practice of remote examination by a professional and/or assessment algorithm.
  • Data may be uploaded via internet connection or can be stored and later uploaded or otherwise provided for analysis to a system, such as machine learning system, or to a professional.
  • Preferred devices enable a patient to self-align or adjust device themselves without the help of a professional, collect and store data and can transmit data when a connection is available to a professional or an analysis system, such as a machine learning system, for evaluation.
  • initial analysis can be provided by software in a preferred system for confirmation or evaluation by a professional and can flag information for a patient if data reveals an urgent condition.
  • a preferred embodiment provides an ophthalmic device including a hand-held housing with an eye facing side, a slit beam lamp associated with the housing for directing a beam of light onto and into the eye of a patient having an eye placed up to the eye facing side, a sensor to image the eye of the patient, and a data interface for providing image data of the camera to ophthalmic analysis software or an ophthalmic professional.
  • Another ophthalmic device includes a hand-held housing that defines contours on its eye facing side contoured to match a patient face and includes two-eye cups for a patient to align the patient’s eyes and optics for directing a beam of light from a slit beam source in the housing to one eye and image data from a display in the housing to another eye.
  • Another ophthalmic device includes housing enclosing magnets to attach the device to a smartphone, a two way mirror positioned by the housing to align with a camera of the smartphone, and a slit light source within the housing and optics to direct a slit light beam onto and into a patient’s eye when the patient is focusing on a reflection of the patient’s eye in the two way mirror.
  • FIG. 1 a schematic cross-sectional view of a hand-held screening device for remote ophthalmic diagnostics according to a preferred embodiment of the invention
  • FIG. 2 a schematic cross-sectional view of a hand-held screening device consistent with FIG. 1 and having additional slit-beam light sources;
  • FIG. 3 a schematic cross-sectional view of a hand-held screening device consistent with FIG. 1 and having slit-beam light sources with multiple elevation angles;
  • FIG. 4A a schematic cross-sectional view of a hand-held screening device consistent with FIG. 1 and having and having a preferred eye cup
  • FIG. 4 B shows a variation of the FIG. 4A device that includes optics for reading intraocular pressure assisted by an implanted intraocular sensor 23;
  • FIG. 5 a schematic cross-sectional view of a hand-held screening device consistent with FIG. 1 and having intraocular pressure measurement;
  • FIG. 6 a schematic cross-sectional view of a hand-held screening device consistent with FIG. 1 and having multiple chambers for multiple diagnostic tests;
  • FIG. 7 illustrates steps taken by a patient using the FIGs. 1-6 hand-held screening devices for remote ophthalmic diagnostics
  • FIGs 8A-8B are perspective view of a hand-held screening device for remote ophthalmic diagnostics that attaches to and interfaces with a smartphone according to a preferred embodiment of the invention
  • FIG 8C is an exploded view of the FIGs. 8A-8B device
  • FIG. 8D is schematic diagram of the FIGs. 8A-8C device
  • FIGs. 8E and 8F are schematic diagrams of a variation of the FIGs. 8A-8D device
  • FIGs. 9A-9C are perspective views of another preferred hand-held screening device for remote ophthalmic diagnostics that attaches to and interfaces with a smartphone.
  • Preferred embodiments of the invention provide ophthalmic devices that can be used in traditional professional office settings or can be used for the practice of remote examination by a professional and/or assessment algorithm. Data may be uploaded via internet connection or can be stored and later uploaded or otherwise provided for analysis to a system, such as machine learning system, or to a professional.
  • a preferred device provides remote ophthalmic examinations and includes one, plural or all of the following capabilities: slit lamp examinations, visual acuity examinations, fundoscopy, and eye pressure assessment.
  • Preferred devices enable a patient to self-align or adjust device themselves without the help of a professional, collect and store data and can transmit data when a connection is available to a professional or an analysis system, such as a machine learning system, for evaluation. With machine learning, initial analysis can be provided by software in a preferred system for confirmation or evaluation by a professional and can flag information for a patient if data reveals an urgent condition.
  • a slit lamp feature allows the patient to turn on the slit light source and shine a slit onto the eye cutting into the anterior chamber, much like the standard slit lamp.
  • a fundus feature allows the patient to direct the light source to the posterior chamber of the eye and view the retina, namely, the fundus, macula, posterior pole, and optic nerve regions.
  • the visual acuity feature allows the patient to take a visual acuity examination and determine the acuity score.
  • a pressure feature allows the patient to take intraocular pressure measurements.
  • a preferred device is internet enabled and would allow for ophthalmologists or physicians to remotely administer eye exams.
  • Benefits of preferred devices include: (1) the device enables remote examination (2) provides the ability to self-focus, adjust, and examine the eye without a skilled secondary person (3) includes modularity and integrative capabilities to tune the examination choices to the patient needs.
  • a patient or physician can administer any of the previously described examinations in any setting. The patient is instructed to look into an eyepiece of the device. A correct light source projection or display will appear and the examination will be performed.
  • a physician can view remotely live, or images can be captured to be reviewed at a later time.
  • Preferred devices provide a“clinic in a box” instrument which any person can use to perform examinations for monitoring purposes of their eye condition. It can also be used as a pocket tool for physicians to perform quick examinations both in person and remotely on patients.
  • Preferred systems and method provide remote ophthalmic screening and follow-up that is inexpensive and convenient. This can enhance medical outcomes while also satisfying economic concerns with examination while allowing patients to self- perform remote screening. This enables more frequent measurements, for example daily, multiple times per day, or even continuously, generating far more data points than available with a clinic-based set-up. Data can be provided to medical professionals, who then have access to more complete patient data without the expense and inconvenience of requiring patient visits and on-site data acquisition.
  • Preferred devices of the invention permit ophthalmic reading and imaging techniques to be carried out by a patient consistently and reliably and provide data that is comparable, or even more comprehensive and accurate, than data obtained by an ophthalmic professional trained to use standard clinical instruments.
  • Devices and systems of the invention provide for measurements including, for example visual acuity, intraocular pressure measurement, biomicroscopy, and evaluation of the posterior pole of the eye.
  • a preferred embodiment device is a hand-held remote ophthalmic screening device.
  • the device includes a substantially closed chamber provided with an eye facing side.
  • a concave mirror is in the chamber and positioned to reflect an image of the eye along an optical path in the chamber back towards the eye facing side, thereby allowing a subject to focus on his or her own eye.
  • the device includes a slit light source positioned to shine a slit onto and into the eye of a patient, a sensor to image portions of the eye illuminated by the slit light source, and memory for storing sensed images.
  • the chamber and mirror are configured such that a patient can position the eye facing side of the device is located in front of a subject’s eye, thereby creating a close-up image of the subject's eye within the focal distance of the eye, hence allowing for an ophthalmic screening process, for example through biomicroscopy,
  • the device has Internet connectivity, thereby facilitating Internet-based imaging, data transfer and communication techniques, through which the status of the eye can be documented without the physical presence of both a doctor and patient in the same room.
  • Preferred devices of the invention also can include data input, such as voice input to record verbal input from a patient, in addition to and in association with data concerning visual acuity, intraocular pressure measurements, bio-microscopy, and evaluation of the posterior segment and in particular the posterior pole of the eye.
  • data input such as voice input to record verbal input from a patient, in addition to and in association with data concerning visual acuity, intraocular pressure measurements, bio-microscopy, and evaluation of the posterior segment and in particular the posterior pole of the eye.
  • Internet connectivity can be through a wired or wireless interface with another device, such as a computer, tablet or smartphone.
  • Systems of the invention can include an app on such a device.
  • the app can include a user interface that provides instructions for conducting a particular test, and a confirmation of when the test has been successful.
  • the app can provide for secure data transfer between a patient and a provider with encrypted communications such as used by medical apps and banking apps. Data handling and storage can be according to local regulations about patient privacy. Additional apps, particularly with regard to visual acuity measurement, glasses and contact lens fitting, can be though a provider that supplies glasses and contact lenses to allow fitting/examination to be conducted remotely.
  • a hand-held remote ophthalmic diagnostics device is configured to allow a patient to focus on his or her own eye and therefore to consistently and reliably position his eye in front of the device to produce an 'in-focus image', enabling subsequent digital imaging and/or measurements.
  • the outer dimensions may vary in size depending on its functionalities and the equipment in its chamber, but it should preferably be portable, preferably not exceeding circa 1-10 kg and more preferably within circa 0.05-1 kg, with outer dimensions preferably not exceeding circa 50x50x50 cm or circa 0.125m 3 , and more preferably within circa lOxlOxlOcm or circa 0.001m 3 .
  • the device 1 may have one or more openings for the subject to look into, with the openings being preferably within circa 50- 100cm 2 or more preferably within circa 15 -25 cm 2 .
  • the hand-held screening device 1 has a substantially closed chamber 2 provided with an eye facing side 3, sidewalls 4a-b and a bottom wall 5 surrounding an interior 21 of the chamber 2.
  • the shown chamber 2 is substantially box-shaped, but may have another geometry, e.g. a cylinder having a circular cross section. Otherwise, the chamber has a cross section that is polygonal, e.g. as a square.
  • the eye facing side 3 may be completely or partially open, preferably having dimensions exceeding the front dimensions of the human eye. However, in principle, the eye facing side 3 may be closed though optically transparent for performing ophthalmic optical measurements or when the device is not in use.
  • a concave mirror 6 accommodated in said chamber 2 is positioned to reflect an image of an eye 70, located in front of the eye facing side 3, along an optical path 8, 9 in the chamber 2 back towards the eye facing side 3 of the chamber 2. Then, a subject looking into the chamber, via the eye facing side 3 and into the concave mirror 6, observes his/her own eye 70.
  • the concave mirror 6 extends in a plane substantially parallel to the eye facing side 3 of the chamber. Then, the image of the eye travels via an optical path 8, 9 that is substantially parallel to the sidewalls 4a-b of the chamber 2.
  • the concave mirror 6 preferably has a focal length in a range from circa 1 cm to circa 1 m, preferably in a range from circa 5 cm to circa 20 cm.
  • a distance between the eye facing side 3 and the concave mirror 6 is in a range between circa 1 cm and circa 1 m, preferably in a range between circa 2 cm and circa 10 cm, more preferably in a range between circa 4 cm and circa 6 cm, e.g. circa 5 cm
  • FIG. 1 A shows a single concave mirror 6
  • multiple concave mirrors can be utilized to permit a patient to focus the device using the best image of his or her own eye using any of multiple projections within the device 1, to account for differences in visual acuity to allow patients to focus on the image.
  • the device 1 can be construed such that if the image of his own eye is in focus for the patient, the image is also in focus for all other readings and imaging elements, for example a slit-beam, a visual acuity display, etc.
  • Camera software can use conventional lens system 'self- focusing' procedures, and any camera should also be positioned within the depth of focus range of the mirror system.
  • the concave mirror 6 should preferably be circa 0.5- 12cm in diameter and more preferably circa 2-5cm in diameter.
  • the mirror 6 should be positioned within the chamber 2 of the device 1 so that it clearly reflects the subject’s own eye, ideally parallel to the eye facing side 3 of the device (or physically oriented at a different angle if multiple mirrors are used, to produce a similar image as with a parallel orientation).
  • the device 1 is preferably used at room temperature or within circa 0-40 degrees
  • the concave mirror 6 preferably is a two-way mirror, as is the case in FIG. 1, thereby allowing the positioning of active optical units such as a camera and/or display screen in the plane of or behind the mirror 6.
  • the mirror may contain a small hole to accommodate the camera, that may be positioned centrally or off-axis, for example in the blind spot of the subject's eye.
  • a camera(s) positioned in the plane of the concave mirror may not interfere with its image formation because they are within the focal distance of the eye).
  • FIG. 1 includes two cameras 7a-b arranged next to each other and behind the concave mirrors 6, opposite to the eye facing side 3. The two cameras are arranged for stereo-imaging of the subject’s eye.
  • a single slit-beam lamp 10 is shown and includes a light source 11, a shield having a slit 12 and a convex lens 13.
  • the light beam is directed in a beam direction BD towards the eye facing side 3 for projecting a slit-beam onto and into the subject’s eye 70 in front of the eye facing side 3.
  • the lamp 10 is preferably positioned out of the line of sight of a subject as shown in FIG. 1, i.e., projected at an angle into the eye away from a location outside the field of view when a subject is using the device 1.
  • the device 1 may optionally include a multiple number of slit- beam lamps 10a- lOg arranged on the sidewalls 4 of the chamber, preferably mainly uniformly distributed in a circular direction around a longitudinal axis L of the chamber 2 oriented transversely to the eye facing side 3 for illuminating the eye 70 from multiple and different circumferential locations, e.g. at various angles, e.g. ranging from 0 to 360 degrees around the longitudinal axis L.
  • the sidewalls 4 generally extend in a transverse direction relative to the eye facing side 3 and substantially parallel to the longitudinal axis L.
  • slit-beam lamps 10a- lOg can be located at different offsets to the eye facing side 3, along the longitudinal axis L, to illuminate the eye 70 at distinct elevational directions with respect to the longitudinal axis L to allow for illumination of superficial or deeper intraocular structures.
  • the slit-beam lamps 10 are arranged on an arc that is rotationally symmetric relative to the longitudinal axis L, e.g. on a single circular contour or semi-circle contour enabling illumination across the eye. Then, the lamps 10 illuminate the eye 70 at the same elevational direction, but from different circular positions around the longitudinal axis L.
  • the slit-beam lamps 10 are arranged on a section running from a first offset position to a second offset position, mainly parallel to the longitudinal axis L, preferably having a specific rotational orientation with respect to the longitudinal axis L. Then, the lamps 10 illuminate the eye at different elevational directions relative to the longitudinal axis for illumination of superficial and deeper intraocular structures.
  • a first set of slit-beam lamps 10 is arranged rotationally symmetric relative to the longitudinal axis L, on a first circular contour
  • a second set of slit-beam lamps 10 is arranged rotationally symmetric relative to the longitudinal axis L, on a second circular contour, closer to or more remote to the eye 70 than the first circular contour, then enabling both circumferential and elevational variation of illuminating beams.
  • the number of lamps can be designed such that the device meets user-specified criteria, e.g. 2, 4, 6, 8, 12 or more lamps.
  • a first set of slit-beam lamps 10a- lOe is arranged on a first arc contour
  • a second set of slit-beam lamps (as an example one lamp lOf is shown) is arranged on a second arc contour AC2 on the sidewall 4, concentric to the first arc contour AC1, at a second projected position P2 on the longitudinal axis L having an offset distance d2 along the longitudinal axis L to the eye facing side 3, closer to the eye facing side 3 than the first set of slit-beam lamps lOa-e.
  • a third set of slit-beam lamps (as an example one lamp lOg is shown) is arranged on a third arc contour AC3 on the sidewall 4, concentric to the first and second arc contour AC2, AC3, at a third projected position P3 on the longitudinal axis L having an offset distance d3 along the longitudinal axis L to the eye facing side 3, more remote than the first and second set of slit-beam lamps lOa-f.
  • the first set of slit-beam lamps lOa-e generate a light beam LB1 having a first elevation angle EA1 relative to the longitudinal axis L
  • the second set of slit- beam lamps lOf generate a light beam LB2 having a second elevation angle EA2 relative to the longitudinal axis L, more or less the same as the first elevation angle EA1 for illuminating more remote internal structures of the eye 70
  • the third set of slit-beam lamps lOg generate a light beam LB3 having a third elevation angle EA3 relative to the longitudinal axis L, also more or less the same as the first and second elevation angle EA1, EA2, for illuminating more superficial internal structures of the eye 70.
  • the device should generate a slit-beam that can focus on various structures of the eye, irrespective of the refractive error of the eye.
  • An examination is better without aids to correct for the refractive error of the eye i.e. glasses or contact lenses, and the distance relative to the mirror and therefore the eye facing side, will vary with the refractive error if the subject is focusing his eye on the concave mirror.
  • This issue is addressed in preferred embodiments, with a system including the convex lens 13 used to focus the slit-beam having a slightly larger depth of focus than the variation in distance from the concave mirror dictated by a normal range of refractive error (e.g., +12D to -12D).
  • multiple slit-beams may be used to correct for the discrepancy in positioning of the subject's eye, whereby each of these slit-beams is focused to correct for a refractive error range, each preferably within 3-6 diopters of refractive error and more preferably with 1-3 diopters.
  • a slit-beam sequence e.g. at 0.5-50Hz
  • the slit-beam(s) may be electronically or mechanically adjusted in height and color.
  • the slit-beam(s) should preferably have a yellow-whitish color, preferably in the range of circa 2700K to 3200K color temperature, but its color may be electronically or mechanically changed to blue or yellow, to allow special examination techniques such as tear film evaluation with cobalt blue filter or yellow barrier filter.
  • FIG. 3 illustrates an alternative configuration of the device shown in FIG.1.
  • a mirror
  • the mirror 14 is located in the chamber 2 at a tilted orientation with respect to the eye facing side 3 and in the optical path 8’, 9’ between the eye facing side 3 and the concave mirror 6’ now located along a sidewall 4a of the chamber 2. Then, the image is reflected by the mirror 14 towards the concave mirror 6', back to the mirror 14 and subsequently back to the eye 70.
  • the mirror 14 is tilted 45° relative to the eye facing side 3 and the concave mirror element 6' is oriented transverse relative to said eye facing side 3.
  • alternative orientations can be implemented such that the image travels from the eye via the mirror 14 towards the concave mirror 6’ and back to the eye 70 via the mirror 14. Further, in FIG.
  • the mirror 14 is mainly flat and two-way, i.e. a beam splitter, the latter allowing active optical units such as camera and display to be located behind said mirror 14.
  • the mirror 6’ can be flat while and the mirror 14 concave.
  • additional mirrors can be included in the optical path from and towards the eye 70.
  • FIG. 3 shows a display element or screen 15 on a sidewall 4b opposite to the concave mirror 6’, behind the two-way mirror 14.
  • a camera 7 is located on the bottom side 5 of the chamber 2. Then, the camera 7 is oriented transverse with respect to the display 15.
  • one or more separate display screens and/or cameras can be applied.
  • optics of a camera can be used as a display.
  • a projection can be established via an optical path 16 from the display screen 15 towards and onto the two-way mirror 14, to create an image behind that mirror, in which case the mirror has to be a two-way mirror in both directions.
  • an image traveling from the two-way mirror 14 via another optical path 17 towards the camera unit 7 can be captured.
  • a projected image may be created at a different portion of the device 1, for example by providing multiple chambers 2 as explained in more detail referring to FIG. 6.
  • the position of the sensors for taking measurements is generally in the vicinity of the cameras, unless a more suitable position is available or indicated.
  • the distance between a central portion of the tilted mirror element 14 and the concave mirror element 6’, the camera unit 7 and the display element 15 is preferably the same or substantially or proportionally the same. In the latter case, the concave mirror may be positioned in an asymmetric manner providing a larger distance to the display and/or camera.
  • FIG. 4A illustrates a preferred annular shaped non-transparent or two-way cup or suction cup 19 attached on the eye facing side 3 of the chamber 2 and extending away from chamber 2.
  • the interior 21 of the chamber 2 is completely closed by the exterior surface of the subject’s eye, and a pressure in the chamber interior 21 can set, independently from the atmospheric pressure.
  • the device 1 further comprises a pressurizer such as a balloon or an automated pressure device for pressurizing the chamber interior 21 for facilitating intraocular pressure measurements as explained in more detail with respect to FIG. 5.
  • the chamber 2 may include an inflating port 18 connected or connectable to the pressurizer, the inflating port being provided with a one-way valve allowing air to flow into the chamber while blocking air to flow outwardly form the chamber.
  • the suction cup 19 may include a deflating port connected or connectable to a de-pressurizer, the deflating port being provided with a one-way valve allowing air to flow outwardly from the suction cup while blocking air to flow inwardly, into the suction cup 19.
  • the suction cup 19 can be provided with a double wall structure defining an interior volume that can be depressurized for sucking the cup 19 against the periocular and/or facial skin 20 of the subject.
  • the material of the cup is flexible enough to create contact the periocular and/or facial skin 20 of the subject and creating an airtight seal.
  • the illumination level within the device can be controlled by the non transparent suction cup 19 positioned onto the periocular skin, so that no ambient light interferes with the imaging of the subject’s eye.
  • The‘ambient light’ within the device can be controlled by providing a diffuse light source arranged in the chamber 2.
  • the suction cup 19 may be construed from a two-way material for light, so that all outside ambient light is blocked while the subject’s eye position can be visualized by an observer, e.g. an instructor explaining the use of the device to a patient.
  • Static letter charts are routinely used in the ophthalmic practice, with smaller letter sizes (smaller angle of resolution) representing higher visual acuities.
  • the device 1 a similar principle may be used to expand on the method both doctors and patients are familiar with.
  • the method may be improved in several ways.
  • the chart shown on the display element 15 may be dynamic through displaying a variable letter size, but with different letters, to prevent visual acuity level bias through recall.
  • the chart may show various shades of contrast and color, to enable simultaneous contrast sensibility and color vision readings.
  • the projector may display the letter size based on an average visual acuity level measured by the device with a specific patient on previous occasions.
  • FIG. 4 B shows a variation of the FIG. 4A device that includes optics for reading intraocular pressure assisted by an intraocular sensor 23.
  • the sensing methods and the sensor 23 can be conducted as in Phan et al., Optical Intraocular Pressure Measurement System for Glaucoma Management, 2017 IEEE Healthcare Innovation Point-of-Care Technologies (HI-POCT) Conference; and as in Phan et al.,“A Wireless Handheld Pressure Measurement System for In Vivo Monitoring of Intraocular Pressure in Rabbits,” IEEE Transactions on Biomedical Engineering (June 24, 2019).
  • FIG. 4B omits some features of FIG.
  • An interference light source 25a with filter 25b, and lens 25c directs light via an additional beam splitter l4 2 to interact with the implanted sensor 23.
  • Pressure on the sensor 23 affects an interference pattern, which is detected via the camera and can be analyzed as in the cited publications. Specifically, interference fringes are formed when the light from the interference light source 25 a interacts with the implanted sensor 23.
  • F1G. 5 illustrates a preferred balloon 22 for pressurizing the chamber interior 21.
  • the device 1 further comprises an additional mirror 24 located in the chamber 2 in a tilted orientation with respect to the eye facing side 3 defining an additional optical path between the eye facing side 3 and an active optical unit, wherein tilting axes AX1, AX2 of the mirror 14 and the additional mirror 24, respectively, are transverse with respect to each other.
  • the tilting axes of mirrors 14 and 24 do not coincide, thereby creating separate optical paths.
  • multiple active optical units such as cameras and/or displays can be made visible, simultaneously, to the user.
  • devices and method of the invention avoid any implanted intraocular devices and can still measure intraocular pressure.
  • devices of the invention for example the preferred FIG. 4B device can also measure intraocular pressure with the assistance of an intraocular implant.
  • a new model using non-contact measurement is preferred by preferred embodiments of the present invention.
  • Devices of the invention can rely on hydration status, as it is has been found that the hydration status of the cornea, crystalline lens and retina varies with the intraocular pressure, rendering specific changes in thickness, diameter, transparency, diffraction and polarization.
  • Devices can rely on blood flow detection, as it has been found that multiple anatomical structures show detectable changes that vary with the intraocular pressure level, for example the arterial and venous blood flow (and the ratio between them), the actual blood volume within the ocular structures like the iris, ciliary body, retina uvea and choroid (squeezing empty effect with higher pressures), muscle contraction and relaxation status and times thereof.
  • intraocular pressure level for example the arterial and venous blood flow (and the ratio between them)
  • the actual blood volume within the ocular structures like the iris, ciliary body, retina uvea and choroid (squeezing empty effect with higher pressures), muscle contraction and relaxation status and times thereof.
  • Techniques for measurements using the present models can include projection of patterns, e.g., concentric rings, onto the cornea, crystalline lens or retina, to allow for contour variations that can indicate the intraocular pressure level through a change in (color) diffraction patterns and higher order aberrations.
  • These methods may be combined with corneal and crystalline lens transparency measurements by densitometry (backward scatter) and stray light measurements (forward scatter), pachymetry and lenticular thickness measurements, as well as corneal, crystalline lens and retinal polarization measurements, to identify threshold values indicating pathology.
  • Sensitivity and specificity can be improved with Doppler flow readings, which can measure the (change in) arterial and venous perfusion throughout the limbal area, the iris, the ciliary body, the retina, the uvea and the choroid, as well as the main vessels entering the eye through the optic disc.
  • Doppler flow readings can measure the (change in) arterial and venous perfusion throughout the limbal area, the iris, the ciliary body, the retina, the uvea and the choroid, as well as the main vessels entering the eye through the optic disc.
  • the ratio between arterial and venous flow was found to be indicative of the (change in) intraocular pressure, since the arterial and venous flow show an asymmetrical reduction with increasing intraocular pressure levels.
  • the blood volume content of various structures can be measured with infrared light, ultrasound and other imaging methods. Additionally, testing can be improved with a pressure- chamber to equalize the intraocular pressure.
  • the pressure can be easily increased inside the device, by compressing a balloon on the outer side of the device or by using an automated pressurizing element, that is coupled via a pressure valve with the interior pressure chamber.
  • an automated pressurizing element that is coupled via a pressure valve with the interior pressure chamber.
  • the corneal contour of the subject’s eye will start to change, most commonly by central indentation, which is registered by diffraction, polarization or refractive power changes, as described above.
  • the suction cup can include a second balloon or automated system to create a negative suction pressure over a double walled suction cup relative to atmospheric conditions, e.g. an underpressure.
  • FIG. 6 illustrates a variation of the preferred device with a pluarlity of substantially closed chambers 2’, 2” each provided with an eye facing side 3’, 3”, and optical components accommodated in said chamber for performing respective measurement on the subject’s eye.
  • Two-way or two-way mirrors 14’, 14” are located in a tilted orientation with respect to the eye facing sides 3’, 3” such as to generate an optical path from the respect eye facing sides, via the mirrors 14’, 14” towards respective concave mirrors 6’, 6” located on a sidewall of the chambers 2’, 2”.
  • Multiple chambers allow, for example, a chamber for visual acuity measurements, another chamber for bio-microscopy and posterior pole imaging, and yet a further chamber for intraocular pressure evaluations.
  • Preferred devices of the invention include a control unit or processor for electronically operating the device 1, more preferably also including a local and remote user interface for selecting operations. Further, the device 1 may have Internet connectivity. All measurements and imaging data obtained can then be digitally transferred to a remote observer location and stored into a database to support the algorithms for detection of anatomical, functional or secondary changes from the data points on average with an increasingly narrow margin to detect relevant ophthalmic deviations and/or pathology. Hence, the system allows the remote observer to examine the subject’s eye through real-time or temporally stored images and measurements, supported by multiple data point analysis of measurements performed since the last or any other prior examination or evaluation.
  • FIG. 7 illustrates steps of a method according to the invention.
  • the method is used for performing screening for remote ophthalmic diagnostics.
  • a step of providing 110 a hand-held screening device to a user is the initial step, and the devices is consistent with FIGs. 1-6.
  • a patient places the patient’s eye 120 the eye facing side of the device in front of a subject’s eye.
  • the control unit then conducts 130 an ophthalmic measurement on the eye.
  • the step of performing an ophthalmic measurement on the eye can be performed using dedicated hardware structures, such as FPGA and/or ASIC components. Otherwise, the method can at least partially be performed using a computer program product comprising instructions for causing a processor of a computer system to perform the above described steps.
  • a number of steps can in principle be performed on a single control unit or processor. However, it is noted that respective ophthalmic measurements can be performed on a separate control unit or processor.
  • a sub-step of driving a display can be carried out by a first processor while a sub-step of controlling operation of a camera unit can be carried out on a second processor.
  • FIGs. 8 A and 8B are perspective views of a preferred embodiment ophthalmic device 200 that leverages a smart phone 202 and includes a hand-held housing 204 defining an eye facing side 206.
  • the eye facing side 206 is shaped and configured with contours 209 to closely fit on a patient’s face, with separate left and right eye cup portions 208 and 210.
  • a holder 214 accepts and holds the smart phone 202, preferably at the comers.
  • the holder 214 can slide open to accept the phone 202 and preferably can lock in multiple positions to accommodate different sizes of smart phones.
  • a user interface 216 includes buttons 218 for activating the device and conducting tests.
  • FIG. 8C is a schematic diagram of the device 200 with the smart phone 202 attached.
  • the device 200 leverages a camera 230 of the smart phone 202 to image eye structures.
  • a two-way concave mirror 232 allows the patient to position the device and focus on his or her own eye. Additionally, the two- way concave mirror 232 allows the camera 230 to image the patient’s eye.
  • the slit lamp includes a light source 234 that emits a beam that passes through a collector lens 236 and slit 238.
  • a projection lens 240 projects a slit beam via angled mirror 242 onto and into a patient’s eye.
  • the mirror 242 can be mounted on a servo or motor 243 (see FIG. 8C) and the mirror’s angle can be modulated so that the slit beam is projected at various locations across the patient’s eye.
  • An LCD screen 244 can present stimulus to a patient’s eye via another angled mirror 246 and a lens 248.
  • the lens 248, preferably is a biconvex with diopter circa 20D - 40D, is integrated to allow patients to focus the display on LCD screen 244 regardless if they are far sighted, near-sighted, or normal.
  • a patient simply turns the device 200 on and presses on a button corresponding to either a slit lamp examination or visual acuity examination to start. The patient then positions their eyes in front of left and right eye cup portions 208 and 210 and begins the examination.
  • a physician can remotely connect to the device camera through a mobile application and review the patient eye remotely without the need of physical presence.
  • the left side of the device 200 can conduct a visual acuity test on a patient’s left eye, and the right side of the device can conduct slit light examination and imaging of the patient’s right eye.
  • the device 200 can be flipped, as it is shaped and contoured to allow the patient to switch testing on the eyes, such that the visual acuity portion of the device can be used with the right eye and the slit light testing with the left eye.
  • FIGs. 8E and 8F show variations of the FIG. 8A device that don’t use a smart phone.
  • FIG. 8E a built-in camera 250 is included (shown separately from the housing for clarity but can be included in the housing itself). Another variation is that the LCD screen 244 is in line with a patient’s eye, so the angled mirror 246 is omitted. Other features are labeled as in FIG. 8C.
  • FIG. 8F modifies FIG. 8E by including a projector 260 in place of the LCD screen 244 to provide visual stimulus through the lens 248.
  • Operations and additional features of the FIGs. 1-6 devices can also be included in the FIGs. 8A-8Fdevices. For example, while one slit light beam and source is shown in FIGs.
  • the housing 204 provides room to additional slit light paths to provide additional slit light beam paths onto and into the eye.
  • the housing 204 and eye cup portions 208 and 210 can seal and the housing 204 can include pressurization features discussed above.
  • An app installed on the smart phone or included in a dedicated hardware/firmware in the housing 204 can provide operations including pressure measurement via Doppler flow readings, as discussed above.
  • FIGs. 9A-9C show another preferred hand-held ophthalmic device 700 that is configured to attach to a smartphone 702, via magnets 704 as shown attached in FIG. 9C.
  • the device 700 includes a two-way concave mirror 706 that is positioned by a housing 708 to align with a camera of the smartphone 702.
  • a slit lamp source 710 such as an LED generates a light beam that is collected by a collection lens 712, which beam is then converted to as slit by a slit structure 714, projected by a projection lens 716 and an angled (or multiple angled) mirror(s) 718.
  • the mirror(s) 718 are positioned below the two-way mirror 706 outside of a field of vision such that the slit light beam can pass onto an into a patient’s eye while the patient is focusing on the reflection of the patient’s eye in the two-way mirror 706.
  • a battery powers the lamp source 710, and can be charged through a charging port 722.
  • a circuit board 724 controls the on and off state of the LED.
  • the ophthalmic device 700 operates as a stand-alone device and can be attached to a phone camera. The functionality of device 700 is preferably irrespective of the app on a phone.
  • a switch 726 turns the device 700 on, and is exposed through a hole 728 in a top cover 730 that closes the device 700.
  • the stand-alone slit device 700 can be integrated into a frame, as shown in FIG. 8C, and connected to the other examinations such as fundus, pressure measurement, and visual acuity to create a multi-function device.

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Abstract

L'invention concerne un dispositif qui fournit des examens ophtalmiques à distance et qui comprend une, plusieurs ou toutes les capacités suivantes : des examens par lampe à fente, des examens d'acuité visuelle, un fond d'œil et une évaluation de la pression oculaire. Des dispositifs préférés permettent qu'un patient auto-aligne ou règle le dispositif lui-même sans l'aide d'un professionnel, collectent et mémorisent des données et peuvent transmettre des données, lorsqu'une connexion est disponible, à un professionnel ou un système d'analyse, tel qu'un système d'apprentissage automatique, pour une évaluation.
PCT/US2019/057618 2018-10-24 2019-10-23 Dispositifs et systèmes de dépistage portables pour diagnostics ophtalmiques à distance WO2020086693A1 (fr)

Priority Applications (4)

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US17/285,946 US20210330186A1 (en) 2018-10-24 2019-10-23 Portable screening devices and systems for remote opthalmic diagnostics
AU2019365201A AU2019365201A1 (en) 2018-10-24 2019-10-23 Portable screening devices and systems for remote opthalmic diagnostics
EP19875120.8A EP3870026A4 (fr) 2018-10-24 2019-10-23 Dispositifs et systèmes de dépistage portables pour diagnostics ophtalmiques à distance
CA3117117A CA3117117A1 (fr) 2018-10-24 2019-10-23 Dispositifs et systemes de depistage portables pour diagnostics ophtalmiques a distance

Applications Claiming Priority (4)

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NLN2021870 2018-10-24
NL2021870A NL2021870B1 (en) 2018-10-24 2018-10-24 A hand-held screening device for remote ophthalmic diagnostics, a method and a computer program product
US201962843059P 2019-05-03 2019-05-03
US62/843,059 2019-05-03

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US20050117118A1 (en) * 2001-10-05 2005-06-02 David Miller Digital ophthalmic workstation
US20070019156A1 (en) 2005-07-15 2007-01-25 California Institute Of Technology Optomechanical and digital ocular sensor reader systems
US20160000324A1 (en) 2013-03-15 2016-01-07 Vasoptic Medical Inc. Ophthalmic examination and disease management with multiple illumination modalities
US20160367135A1 (en) * 2015-06-18 2016-12-22 David Myung Adapter for retinal imaging using a hand held computer
WO2017180965A1 (fr) * 2016-04-15 2017-10-19 The Regents Of The University Of California Appareil de visualisation de cellules rétiniennes
US20180153399A1 (en) 2015-05-05 2018-06-07 Arizona Board Of Regents On Behalf Of The University Of Arizona Smartphone-based handheld ophthalmic examination devices
US20180153402A1 (en) * 2016-12-07 2018-06-07 Gabriela Roxana SAIDMAN Portable retinography device
US20190133435A1 (en) * 2017-11-06 2019-05-09 SA Photonics, Inc. Mobile ophthalmic device

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Publication number Priority date Publication date Assignee Title
US20050117118A1 (en) * 2001-10-05 2005-06-02 David Miller Digital ophthalmic workstation
US20070019156A1 (en) 2005-07-15 2007-01-25 California Institute Of Technology Optomechanical and digital ocular sensor reader systems
US20160000324A1 (en) 2013-03-15 2016-01-07 Vasoptic Medical Inc. Ophthalmic examination and disease management with multiple illumination modalities
US20180153399A1 (en) 2015-05-05 2018-06-07 Arizona Board Of Regents On Behalf Of The University Of Arizona Smartphone-based handheld ophthalmic examination devices
US20160367135A1 (en) * 2015-06-18 2016-12-22 David Myung Adapter for retinal imaging using a hand held computer
WO2017180965A1 (fr) * 2016-04-15 2017-10-19 The Regents Of The University Of California Appareil de visualisation de cellules rétiniennes
US20180153402A1 (en) * 2016-12-07 2018-06-07 Gabriela Roxana SAIDMAN Portable retinography device
US20190133435A1 (en) * 2017-11-06 2019-05-09 SA Photonics, Inc. Mobile ophthalmic device

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Title
See also references of EP3870026A4

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