Near-to-eye displays within head mounted devices offer both users with and without visual impairments enhanced visual experiences either by improving or augmenting their visual perception. Unless the user directly views the display without intermediate optical elements then the designer must consider chromatic as well as other aberrations. Within the prior art the optical train is either complex through additional corrective elements adding to weight, cost, and size or through image processing. However, real time applications with mobile users require low latency to avoid physical side effects. Accordingly, it would be beneficial to provide near-to-eye displays mitigating these distortions and chromatic aberrations through pre-distortion based electronic processing techniques in conjunction with design optimization of the optical train with low weight, low volume, low complexity, and low cost. Further, it would be beneficial to exploit consumer grade low cost graphics processing units rather than application specific circuits.

Systems and methods for auto-calibrating a virtual reality (VR) or augmented reality (AR) head-mounted display to a given user with a refractive condition without adding corrective lenses to optical elements of the head-mounted display and without requiring subjective refraction procedures. A method comprises projecting a grid onto an eye of a user using a light source of a head-mounted display worn by the user, capturing the grid as-reflected from the eye using a camera of the head-mounted display, determining a pattern of a reflection of the grid based on the grid as-reflected, generating an aberration map based on a difference between the pattern as-reflected and the grid as-projected, and determining a correction to apply to at least one viewing lens of the head-mounted display worn by the user based on the aberration map.

Methods and devices are provided to obtain refractive correction with superior visual acuity (e.g., 20/10) by achieving an astigmatism-free customized refractive correction. The astigmatism-free customized refractive correction involves obtaining an objective and precise measurement of cylindrical power in a resolution between 0.01 D and 0.10 D in an eye using an objective aberrometer, reliably relating the cylindrical axis obtained from the objective aberrometer to that in a phoroptor, determining an optimized focus error of an eye through subjective refraction with a phoroptor, generating a customized refraction by combining the objective measured cylindrical power, the objective measured cylindrical axis, and the subjectively measured focus power, fabricating a custom lens with a tolerance finer than 0.09 D based on the generated customized refraction, and delivering an ophthalmic lens that can provide an astigmatism-free refractive correction for an eye.

Methods, devices, and systems are disclosed for determining refractive corrections of human eyes to reduce and eliminate image distortion associated with eyeglasses. In some embodiments, an objective refraction module is configured to measure refractive errors of an eye objectively, without subjective feedback from a tested subject. A computation module is configured to generate a plurality of objective prescriptions. A phoropter module is configured to perform a subjective refraction for determining a plurality of subjective spherical powers based on the plurality of objective prescriptions. An output module is configured to generate a plurality of prescriptions for eyeglasses, the plurality of prescriptions comprising (a) a first prescription having a first subjective spherical power f.sub.s1, a first objective cylinder power F.sub.c1, and a first objective cylinder angle F.sub.a1, and (b) a second prescription having a second subjective spherical power f.sub.s2, a second objective cylinder power F.sub.c2, and a second objective cylinder angle F.sub.a2.

A technique for driving emmetropization of an eye includes receiving image data corresponding to a color image; blurring a first color channel of the image data greater than a second color channel of the image data in at least a portion of the color image to provide a simulated longitudinal chromatic aberration (LCA) in the portion of the color image; and displaying the color image with the simulated LCA to provide an emmetropization therapy to the eye.

Multifocal intraocular lens with extended depth of field that comprises, in at least one of the surfaces (2), a small zone with a multifocal profile with a defined optical axis (3) and, in the peripheral region and coaxial to the multifocal zone, a ring-shaped opaque mask (1) that partially or totally block light to produce a small aperture effect and, therefore, the multifocal profile has a radius equal or larger than the internal radius of the mask (1), and there is at least one transition between focal zones or one diffractive step inside the internal radius of the mask (1).

Apparatuses, systems and methods for providing improved intraocular lenses (IOLs), include features for reducing side effects, such as halos, glare and best focus shifts, in multifocal refractive lenses and extended depth of focus lenses. Exemplary ophthalmic lenses can include a continuous, power progressive aspheric surface based on two or more merged optical zones, the aspheric surface being defined by a single aspheric equation. Continuous power progressive intraocular lenses can mitigate optical side effects that typically result from abrupt optical steps. Aspheric power progressive and aspheric extended depth of focus lenses can be combined with diffractive lens profiles to further enhance visual performance while minimizing dysphotopsia effects. The combination can provide an increased depth of focus that is greater than an individual depth of focus of either the refractive profile or the diffractive profile

A multifocal ophthalmic lens has an optic zone that includes at least one first zone having a dioptric power that satisfies a distance refraction need of a patient; and at least one second zone having a dioptric power that is greater than the dioptric power of the at least first zone. The at least one first zone and the at least one second zone are configured so that 1) an image quality on the retina of the patient is superior to the image quality both in front of the retina and behind the retina, and 2) an image quality in front of the retina of the patient is superior to the image quality behind the retina. The multifocal ophthalmic lens prevents and/or slows myopia progression.

The embodiments disclosed herein include improved toric lenses and other ophthalmic apparatuses (including, for example, contact lens, intraocular lenses (IOLs), and the like) and associated method for their design and use. In an embodiment, an ophthalmic apparatus (e.g., a toric lens) includes one or more angularly-varying phase members comprising a diffractive or refractive structure, each varying the depths of focus of the apparatus so as to provide an extended tolerance to misalignment of the apparatus when implanted in an eye. That is, the ophthalmic apparatus establishes an extended band of operational meridian over the intended correction meridian.

The embodiments disclosed herein include improved toric lenses and other ophthalmic apparatuses (including, for example, contact lens, intraocular lenses (IOLs), and the like) that includes one or more refractive angularly-varying phase members, each varying depths of focus of the apparatus so as to provide an extended tolerance to misalignments of the apparatus. Each refractive angularly-varying phase member has a center at a first meridian (e.g., the intended correction meridian) that directs light to a first point of focus (e.g., at the retina of the eye). At angular positions nearby to the first meridian, the refractive angularly-varying phase member directs light to points of focus of varying depths and nearby to the first point of focus such that rotational offsets of the multi-zonal lens body from the center of the first meridian directs light from the nearby points of focus to the first point of focus.