Photon biological regulation treatment system and method for head-mounted equipment

Abstract

The invention discloses a photon biological regulation treatment system for head-mounted equipment. The system comprises a control unit, an eye illumination optical unit and an eye imaging optical unit, the eye illumination optical unit configuration working mode comprises a photon biological regulation treatment working mode and an eye biological tissue illumination working mode; the eye imaging optical unit configuration working mode comprises a photon biological regulation feedback monitoring working mode and an eye biological tissue imaging working mode; the control unit is configured to be in a first combined working mode, the eye illumination optical unit is configured to be in an eye biological tissue illumination working mode, and the eye imaging optical unit is configured to be in an eye biological tissue imaging working mode; the control unit is configured to be in a second combination mode of operation, the eye illumination optical unit is configured to be in a photonic bioregulation treatment mode of operation, and the eye imaging optical unit is configured to be in a photonic bioregulation feedback monitoring mode of operation.

Description

Technical Field

[0001] This invention relates to a head-mounted device, and more specifically, to a photonic biomodulation therapy system and method for use in a head-mounted device. Background Technology

[0002] With the development of artificial intelligence (AI) technology in recent years, the popularity of content creation and distribution has significantly increased. Specifically, extended reality (XR)—including virtual reality (VR), augmented reality (AR), mixed reality (MR), or some combination and / or derivative thereof (such as AI glasses)—has developed alongside virtual environments (e.g., the "metaverse"). The integration of AI into these areas can be combined with applications, products, accessories, services, or some combination thereof. Against this backdrop, various applications based on individual eye physiological attributes have received widespread attention. Their application areas include, but are not limited to: eye tracking (ET) gaze direction / position detection, biometrics and health status monitoring, and healthcare. Summary of the Invention

[0003] The purpose of this invention is to provide a photon biomodulation therapy system and method for head-mounted devices.

[0004] The ocular biological tissues of this invention include, but are not limited to, individual physiological attributes such as the eye / iris, retina, subcutaneous tissue of the eye, ocular arteries / veins, and sclera.

[0005] According to some implementation schemes, a device for applying individual eye physiological attributes to a head-mounted device includes: an eye imaging optical unit, an eye illumination optical unit, and a control unit.

[0006] According to some implementations, the eye imaging optical unit includes an image sensor and an imaging lens; the eye imaging optical unit is configured to image directly or indirectly from a predetermined imaging region of ocular biological tissue.

[0007] According to some implementation schemes, the eye imaging optical unit is configured with an angle conversion optical element to convert the incident angle range into a corresponding exit angle range within a predetermined imaging field of view; the incident angle range and the exit angle range are configured with a predetermined angle conversion relationship.

[0008] According to some implementations, the angle conversion optical element is configured with the principal optical axis of the imaging optical unit as the normal axis of symmetry.

[0009] The angle conversion optical element is configured with a predetermined low-order wavefront phase modulation function.

[0010] According to some implementation schemes, the angle conversion optical element is configured with a first-order wavefront phase modulation function.

[0011] According to some implementations, the angle conversion optical element is configured with optical conjugation.

[0012] According to some implementations, the angle conversion optical element is configured with an exit angle range that is symmetrical about the center of the principal optical axis.

[0013] According to some implementations, the angle conversion optical element is configured with angular optical compression from the incident angle range to the exit angle range.

[0014] According to some implementation schemes, the range of the exit angle is less than or equal to the range of the incident angle.

[0015] According to some implementation schemes, the eye imaging optical unit is further configured with a joint imaging mode, wherein the angle conversion optical element and the imaging lens are arranged in a cascaded manner.

[0016] According to some implementation schemes, in the combined imaging mode, the emission angle range is configured as the field of view of the imaging lens.

[0017] According to some implementations, in the joint imaging mode, the imaging lens is configured to focus onto the image plane of the image sensor through an image-side mesocentric structure.

[0018] According to some implementations, in the combined imaging mode, the angle conversion optics are configured as an aperture stop located at the front focal plane of the imaging lens.

[0019] According to some implementations, the angle conversion optical element is configured as a metasurface optical element or a diffractive optical element.

[0020] According to some implementations, the imaging lens is configured as a superlens or a wafer-level optical imaging lens.

[0021] According to some embodiments, the eye illumination optical unit is configured to emit light having at least one polarization state toward the eye.

[0022] According to some embodiments, the eye imaging optical unit is configured to capture images using the image sensor that is sensitive to at least one corresponding polarization state.

[0023] According to some implementations, the control unit is configured to generate at least one identical and orthogonal combination of polarization states, synchronize timing, and process polarization intensity data from the image.

[0024] According to some implementations, the polarization intensity data is configured with at least one of corneal polarization interference intensity mode and / or scleral polarization scattering intensity pattern mode as a cross-reference feature characterizing the physiological state of the eye.

[0025] According to some implementation schemes, the eye imaging control unit is configured to pre-train a high-dimensional mapping dataset of the cross-reference features using a lightweight machine learning / deep learning model to perform end-to-end predictive inference and output dynamic qualitative / quantitative monitoring and analysis of the physiological state of the eye.

[0026] According to some implementation schemes, the cross-reference feature configuration is defined based on manual feature extraction or autonomous high-dimensional feature extraction through dual-channel or multi-channel feature decoupling blocks in machine learning / deep learning models.

[0027] According to some implementations, the eye imaging control unit is equipped with a fixation system that projects a predetermined pattern as a guide for gaze, analyzes image data, and provides feedback and adjustment prompts.

[0028] According to some implementations, the eye illumination optical unit is configured to have multiple wavelengths and multiple polarization states in the visible and near-infrared spectral ranges, and the eye imaging optical unit is configured with corresponding pixelated multi-wavelength channel filters to capture images with multiple wavelengths and multiple polarization states.

[0029] The polarization state is provided by a metasurface grating having a predetermined orientation, subwavelength period, and depth.

[0030] According to some implementations, the eye imaging optical unit is configured with a metasurface-based optical element, which can be configured as a pixel-level polarization focusing spectral router for an image sensor, performing optical modulation function multiplexing of the pixel channel wavelength dimension and polarization dimension for incident light.

[0031] According to some implementations, the eye illumination optical unit and / or eye imaging optical unit may be configured with metasurface-based optical elements, which may be configured to perform optical modulation functions of orbital angular momentum (OAM) mode, wavelength dimension, and polarization dimension on incident light in any combination.

[0032] According to some implementation schemes, a photon biomodulation therapy system is disclosed, comprising:

[0033] Control unit, eye illumination optical unit, eye imaging optical unit;

[0034] The eye illumination optical unit is configured with the following working modes: photon biomodulation therapy working mode and eye biotissue illumination working mode;

[0035] The eye imaging optical unit is configured with the following working modes: photon biomodulation feedback monitoring working mode and eye biological tissue imaging working mode.

[0036] The control unit is configured in a first combined working mode for acquiring images of ocular biological tissues. In response to the first combined working mode, the ocular illumination optical unit is configured in an ocular biological tissue illumination working mode and the ocular imaging optical unit is configured in an ocular biological tissue imaging working mode.

[0037] The control unit is configured in a second combined operating mode for photonic biomodulation therapy. In response to the second combined operating mode, the eye illumination optical unit is configured in a photonic biomodulation therapy operating mode and the eye imaging optical unit is configured in a photonic biomodulation feedback monitoring operating mode.

[0038] According to some implementation schemes, the control unit detects the eye closure state and photonic biomodulation therapy radiation dose in real time through the photonic biomodulation feedback monitoring working mode of the eye imaging optical unit, and uses the feedback to activate or deactivate the photonic biomodulation therapy working mode of the eye illumination optical unit. The power density of the photonic biomodulation therapy working mode of the eye illumination optical unit is greater than that of the eye biological tissue acquisition working mode.

[0039] According to some implementations, the eye illumination optical unit and / or eye imaging optical unit may be configured with metasurface-based optical elements, which may be configured to perform optical modulation functions of orbital angular momentum (OAM) mode, wavelength dimension, and polarization dimension on incident light in any combination.

[0040] According to some implementation schemes, a photonic biomodulation therapy method is disclosed, including:

[0041] Control unit, eye illumination optical unit, eye imaging optical unit;

[0042] The control unit is configured with a first combined operating mode, and responds to the first combined operating mode.

[0043] The eye illumination optical unit is configured in an eye biological tissue illumination working mode and the eye imaging optical unit is configured in an eye biological tissue imaging working mode to acquire eye biological tissue images;

[0044] Assess current eye health status by analyzing images of ocular biological tissues using deep learning algorithms;

[0045] and / or obtain historical medical and health record data;

[0046] The control unit responds to the current eye health status and / or historical medical health record data to generate relevant treatment prescription parameters for photonic biomodulation;

[0047] The control unit responds to the treatment prescription parameters and configures a second combined working mode, wherein the eye illumination optical unit is configured as a photon biomodulation therapy working mode and the eye imaging optical unit is configured as a photon biomodulation feedback monitoring working mode.

[0048] The control unit activates the feedback monitoring working mode of the eye imaging optical unit and simultaneously activates the photon biomodulation therapy working mode of the eye illumination optical unit.

[0049] After completing the relevant prescription treatment for photonic biomodulation, the control unit deactivates the eye illumination optics unit and the eye imaging optics unit, and creates a treatment log, which is stored as historical medical and health record data.

[0050] According to some implementation schemes, the historical medical and health record data is encrypted and stored in local non-volatile memory or uploaded to a specific encrypted data cloud for medical and health record data recording.

[0051] According to some implementation schemes, the prescription parameters for photon biomodulation-related therapy include at least:

[0052] Radiation wavelength, radiation dose, radiation pulse structure, and radiation optical properties data attributes.

[0053] The radiation wavelengths are configured to include: yellow light 570-590 nm, green light 495-570 nm, red light 620-700 nm, near-infrared light 700-1100 nm, or any combination of the above wavelengths.

[0054] The radiation dose includes: energy density, irradiance parameter, and radiation exposure time; the energy density parameter is configured to range from 0.1 to 50 J / cm², and the irradiance parameter is configured to range from 1 to 50 mW / cm². 2 between.

[0055] The radiation exposure time range is configured to be between 30 and 900 seconds.

[0056] The radiation pulse structure is configured to operate in a frequency range of 1-10 Hz and a duty cycle of 10-50%.

[0057] The radiation optical properties are configured as: coherent state, optical polarization state 0°, 90°, 45°, 135°, RCP, LCP or a combination thereof, and orbital angular momentum (OAM) mode.

[0058] The prescription parameters for photon biomodulation-related therapy are configured as a multi-wavelength combination working mode, which can be configured to allow different wavelengths to perform sequential or superimposed accumulation with different irradiance and radiation exposure time. Attached Figure Description

[0059] Figure 1 This is a schematic diagram of direct imaging in AI / AR glasses.

[0060] Figure 2 This is a schematic diagram of indirect imaging in AI / AR glasses.

[0061] Figure 3a / 3b / 3c are schematic diagrams of retinal illumination / imaging of the head-mounted device in Example 1.

[0062] Figure 4 This is a schematic diagram of retinal illumination / imaging for the head-mounted device in Example 2.

[0063] Figure 5 Images illustrating polarization interference and polarization scattering pattern modes of illumination / imaging with combinations of polarization states (parallel and orthogonal).

[0064] Figure 6 This is a schematic diagram of retinal illumination / imaging for the head-mounted device in Example 3.

[0065] Figure 7 This is a schematic diagram of retinal illumination / imaging for the head-mounted device in Example 4.

[0066] Figure 8 Partial scanning electron microscope (SEM) images illustrating the superlens (left) and metasurface grating structure (right).

[0067] Figure 9 Images illustrating polarization interference and polarization scattering pattern modes of different polarization state combinations of illumination / imaging.

[0068] Figure 10a / 10b is a schematic diagram of a 1D and 2D metasurface pixel-level polarization focusing spectral router.

[0069] Figure 11 This diagram illustrates the configuration of an illumination / imaging image based on polarization interference and polarization scattering from a single-mode polarized VCSEL illumination source. Detailed Implementation

[0070] The present invention will now be described in further detail with reference to the accompanying drawings and embodiments, but this should not be construed as limiting the invention in any way.

[0071] The structures, geometric proportions, angles, orientations, arrangement sequences, relative spatial positions, and other attributes shown in the accompanying drawings are illustrative in nature and are not intended to limit the scope of the claims. The invention can be practiced in various ways and should not be construed as limited to the embodiments set forth herein. Rather, these embodiments are provided to ensure thoroughness and completeness of the invention and to fully convey its scope to those skilled in the art. Throughout the specification, the same reference numerals designate the same elements. Furthermore, in the drawings, the thickness, proportions, and dimensions of elements may be exaggerated or reduced for clarity of illustration. The terminology used herein is for the purpose of describing particular embodiments only and is not intended to be limiting. As used herein, the singular forms “a,” “an,” and “described” are intended to include the plural forms as well, unless the context clearly indicates otherwise. For example, “one element” has the same meaning as “at least one element,” unless the context clearly indicates otherwise. The term “at least one” should not be construed as limited to the quantity “one.” The terms “ / ” and “or” mean “and / or.” The term “and / or” includes any and all combinations of one or more of the associated listed items. Unless otherwise defined, all terms used herein, including technical and scientific terms, shall have the same meaning as commonly understood by one of ordinary skill in the art. Terms defined in common dictionaries shall be interpreted as having the meaning consistent with their meaning in the relevant technical context and shall not be interpreted in an idealized or overly formal sense unless expressly defined in the specification. The terms “comprising” or “including” specify the presence of the stated feature, integer, step, operation, element, component, or group thereof, but do not exclude the presence or addition of one or more other features, integers, steps, operations, elements, components, or groups thereof. In this invention, the angle of a light beam (e.g., an outgoing or incoming beam) relative to the surface normal may be defined as positive or negative, depending on the angular relationship between the direction of propagation of the beam and the surface normal. For example, a positive angle may be defined when the direction of propagation is clockwise relative to the normal, and a negative angle may be defined when it is counterclockwise relative to the normal. However, the definitions in this invention are not limited to this convention. In this invention, coordinates (X / Y / Z) or radial directions relative to the origin or principal optical axis may be defined as positive or negative. For example, when the coordinate or radial direction is right / up / forward relative to the origin or principal optical axis, it is defined as positive; when it is left / down / backward relative to the origin or principal optical axis, it is defined as negative. Coordinate systems can be equivalently transformed (e.g., between polar / spherical coordinate systems and Cartesian coordinate systems), although the definitions in this invention are not limited to such conventions. In this invention, terms used to describe actions that alter the optical response of light, such as “transmission,” “reflection,” “absorption,” “shielding,” “blocking,” or similar terms referring to light processing, mean that a major portion (including all) of the light is transmitted, reflected, absorbed, shielded, blocked, etc."Main portion" can be a predetermined percentage of the total light greater than 50%, such as 100%, 95%, 90%, 85%, 80%, etc., which can be determined based on the requirements of a specific application. As used herein, words such as "slightly," "about," "approximately," "substantially," "usually," "nearly," etc., are used as approximate terms rather than terms of degree and are intended to explain the inherent variations in measured or calculated values ​​that will be recognized by those skilled in the art. This specification includes references to "one embodiment" or "an embodiment." The appearance of the phrase "in one embodiment" or "in an embodiment" does not necessarily refer to the same embodiment. Specific features, structures, or characteristics can be combined in any suitable manner consistent with the invention. The term "comprising" is open-ended. As used in the claims, the term does not exclude the presence of additional structures or steps. "Configured to": Various units, functions, or other components can be described or claimed to be "configured to" perform one or more tasks. In such a context, the term "configured to" means that the unit / function / component includes a structure (e.g., an optical path) capable of performing the specified task during operation. Furthermore, "configured to" may also involve adjusting the manufacturing process (e.g., within a semiconductor manufacturing facility) to produce equipment suitable for performing or carrying out one or more tasks (e.g., photonic integrated circuits). "First," "Second," etc. As used herein, these terms serve as labels for the nouns they modify and do not imply any type of order (e.g., spatial, temporal, logical, etc.). The terms "first" and "second" do not necessarily require the first value to be written before the second. "Based on" or "depending on." As used herein, these terms are used to describe one or more factors that influence the determination. These terms do not exclude additional factors that may influence the determination. That is, the determination may be based entirely on those factors, or at least partially on those factors. Consider the phrase "A is determined based on B." While B is a factor influencing the determination of A in this case, such a phrase does not exclude the determination of A from also being based on C. In some instances, A may be determined solely based on B. "Or." When used in claims, the term "or" is used as an inclusive "or," not an exclusive "or." For example, the phrase "at least one of x, y, or z" means any one of x, y, and z, and any combination thereof. It should be noted that, unless otherwise specified, the embodiments and features described in this application can be combined with each other.

[0072] The individual ocular physiological attributes of the embodiments of this application include, but are not limited to, biological tissues such as the eye / iris, retina, subcutaneous tissue of the eye, ocular artery / vein, and sclera.

[0073] In all embodiments, the term "eye illumination / imaging optical unit" is a generalized expression and should include, but is not limited to, the specific ocular biological tissues mentioned above, such as iris illumination / imaging optical units, retinal illumination / imaging optical units, scleral illumination / imaging optical units, periocular subcutaneous tissue illumination / imaging optical units, ocular artery / vein illumination / imaging optical units, etc.

[0074] In some embodiments with equivalent changes, while maintaining consistency with the principles of other embodiments, such as Figure 1 As shown, the eye imaging optics and eye illumination optics of a head-mounted device (e.g., AI / AR glasses 1101) may be subject to size limitations, requiring dimensions smaller than 2mm × 2mm × 2mm. Due to the compact form factor of the HMD (e.g., AI / AR glasses 1101), which necessitates a spatially complex and variable structural layout design, the eye imaging optics 1105A and 1105B can be configured for off-axis arrangement and mounted in different spatial locations and orientations, such as those defined by the temples 1104 and / or the nose pad support 1108.

[0075] In this embodiment, at least one or more eye imaging optical units 1105A and 1105B are configured according to the application scenario, and the corresponding off-axis arrangements are installed at at least one or more spatial locations and orientations. Similarly, in this embodiment, at least one or more eye illumination optical units 1106A and 1106B are configured according to the application scenario, and the corresponding off-axis arrangements are installed at at least one or more spatial locations and orientations.

[0076] The eye imaging optical unit has an imaging field of view (FOVi) corresponding to a predetermined imaging region 1103 (RXi, RYi), including its horizontal (FOVxi) and vertical (FOVyi) components, which are determined by the spatial mounting position of the associated off-axis layout.

[0077] The predetermined tilt angles of the principal optical axes 1100A, 1100B, and 1100C of the eye imaging optical unit corresponding to the predetermined imaging region 1103 (RXi, RYi) are determined by the spatial orientation of the relevant off-axis mounting configuration.

[0078] In a preferred embodiment, for ease of use Figure 1 The explanation is simplified, and the spatial direction of the predetermined tilt angle is used as the principal optical axis 1100A, 1100B, 1100C, which is parallel to the predetermined imaging area 1103 (object plane).

[0079] For ease of subsequent description, the abbreviations AOI (Angle of Incidence) and AOE (Angle of Exit) may be used where appropriate.

[0080] The AOI / AOE (ωi / ωo) range of the eye imaging optical unit corresponding to a predetermined FOVi is determined by the principal optical axis of the eye imaging optical unit at a predetermined tilt angle, which serves as the normal axis of the center of symmetry.

[0081] In other words, the angular range of AOI / AOE (ωi / ωo) is determined by the angular relationship between the principal optical axis (the normal axis as the center of symmetry) of the eye imaging optical unit at a predetermined tilt angle and the predetermined imaging field of view (FOVi).

[0082] To better understand the corresponding AOI / AOE (ωi / ωo) angle range, please refer to [reference needed]. Figure 1 The range shown:

[0083] ωi ∈ [ωis, ωie] and ωo ∈ [ωos, ωoe].

[0084] ωis and ωie represent the boundary range of the AOI.

[0085] ωos and ωoe represent the boundary range of AOE.

[0086] In some embodiments, the variable range of off-axis AOI can be achieved by configuring different predetermined tilt angles for the eye imaging optical unit relative to the principal optical axis (the normal axis at the center of symmetry) of a predetermined FOVi. Some examples of angle ranges for off-axis AOI include, but are not limited to: ωi ∈ [0, FOVi], ωi ∈ [90 - FOVi, 90].

[0087] In some embodiments, consistent with other embodiments, the metasurface optics element (superconverter 1108) that manipulates the AOI / AOE (ωi / ωo) angle transformation of the eye imaging optics unit executes the angle transformation relationship of the wavefront phase modulation function φ (phase gradient φ'). However, as described in other embodiments, the higher-order nonlinear angle transformation relationship of the wavefront phase modulation function may increase the fabrication complexity of the metasurface optics element (superconverter) and may introduce imaging aberrations when operating in joint imaging mode.

[0088] As described in other embodiments, the angle transformation relationship of the wavefront phase modulation function φ (phase gradient φ') in a metasurface optical element (superconverter) can be further simplified to an approximate low-order angle transformation relationship. In some embodiments, it can be configured as a first-order angle transformation relationship with corresponding optical properties while maintaining optical conjugate properties.

[0089] A specific phase profile distribution is configured by manipulating the wavefront phase modulation function (Φ) of a metasurface optical element (superconverter), characterized by the gradient of the wavefront phase modulation function (phase gradient Φ'). The principal optical axis of the eye imaging optical unit is configured as the symmetry center normal axis of the metasurface optical element (superconverter).

[0090] An example illustrates the wavefront phase modulation function Φ (phase gradient Φ') of a superconductor, which has optical properties with a specific first-order angle transformation relationship:

[0091]

[0092] Where k = 2π / λ is the wavenumber, and λ is the imaging wavelength. It is the refractive index of the incident medium (usually air).

[0093] Metasurface optical elements (super converters) establish bijective mapping between AOI and AOE.

[0094] Metasurface optical elements (superconverters) manipulate the angle conversion relationship between AOI and AOE (ωi / ωo), and their optical properties are characterized as follows:

[0095]

[0096] in, It is the refractive index of the exit medium (usually air or relay optical medium). It is the refractive index of the incident medium.

[0097] In this example, the angle transformation properties between ωi and ωo have optical conjugation properties.

[0098] Metasurface optical elements (superconverters) manipulate angle conversion such that when ωi is coupled to the boundary of AOI (ωis / ωie), the boundary of AOE corresponding to ωo (ωos / ωoe) ​​is:

[0099]

[0100]

[0101] This indicates that when ωi is coupled to the boundary (ωis / ωie) of the AOI, the transformed AOE (ωos / ωoe) ​​satisfies ωos = -ωoe, exhibiting perfect centrosymmetric optical properties relative to the principal optical axis of the eye imaging optical unit.

[0102] In a specific example, such as FOVi = 60 degrees and ni / no = 1.0, based on a predetermined imaging field of view (FOVi) and configuring the principal optical axis of the eye imaging optical unit as the normal axis (center of symmetry) at different predetermined tilt angles, a variable range of off-axis AOI can be achieved. For example: ωi∈[0, 60], ωi∈[20, 80], or ωi∈[30, 90].

[0103] when When coupled to the boundary, the angle transformation couples out the corresponding AOE ωo, as shown in the following examples: ωo∈[-25.66, +25.66], ωo∈[-18.75, +18.75], ωo∈[-14.5, +14.5].

[0104] The examples above are merely illustrative explanations of the basic principles and do not constitute exclusive limitations. Different variations with equivalent generalized principles may exist and be implemented.

[0105] By converting the angle of the AOI / AOE beam, the eye imaging optics unit can effectively perform the inverse transformation of the optical properties of off-axis imaging. By controlling the outgoing beam to approximate the physical properties of coaxial geometrical optical imaging, it substantially improves key optical parameters, including imaging region perspective and field of view distortion.

[0106] In addition, the angular range of AOE has:

[0107] (1) Centrally symmetric optical characteristics relative to the principal optical axis of the eye imaging optical unit;

[0108] (2) Optical conjugation properties;

[0109] (3) Optical compression of angular range, wherein the angular range of AOE is less than or equal to the angular range of AOI.

[0110] In the optical path, the AOE angular range from the superconverter 1108 can be optically relayed and used as the FOV of the superlens 1109. This configuration greatly facilitates the optimization of the subsequent focusing optical path, thereby improving the overall optical performance of the imaging system. The spatial resolution (MTF) at the focal plane of the imaging system is strongly dependent on the incident angle range.

[0111] Consistent with other descriptions, Figure 1 This describes how, in the combined imaging mode, the superconverter 1108 is configured to manipulate the AOI / AOE conversion in the optical path. The angular range of the AOE is optically relayed and used as the imaging field of view (FOV) of the superlens 1109.

[0112] The superlens 1109 is configured to focus onto the image plane of the image sensor 1110 using a combined imaging mode.

[0113] In some embodiments used for joint imaging modes, the superlens 1109 is configured to manipulate the AOI / AOE to be focused onto the image plane of the image sensor 1110 in an image-side mesocentric configuration, and the superconverter 1108 acts as the aperture stop of the superlens 1109.

[0114] By utilizing the characteristic that the aperture stop is located in front of the focal plane of the superlens 1109, pericentric imaging within the incident field of view is configured, and off-axis aberrations are manipulated by physical spatial separation (e.g., air gap or optical medium).

[0115] Figure 8 (Left) shows a partial SEM pattern of the subwavelength superatomic nanostructure of the superlens 1109.

[0116] In other embodiments used for joint imaging modes, the superlens 1109 is configured with a wavefront phase modulation function (phase profile distribution) that has a secondary phase profile to provide a virtual aperture stop function.

[0117] In other examples, the predetermined angle conversion optical element includes, but is not limited to, metasurface-based superconverters. Other types, such as diffractive optical elements (DOEs), can perform angle conversion relationships corresponding to a specific wavefront phase profile function (e.g., converting an AOI to an AOE via a diffraction grating equation) by configuring parameters such as diffraction order, periodic feature size, and phase order.

[0118] In other equivalent embodiments, the imaging lens includes, but is not limited to, a superlens. The WLO imaging lens is manufactured using standard CMOS semiconductor processes, such as etching / lithography, imprinting, embedding, UV curing, dicing, and packaging for various optical semiconductor materials. The WLO imaging lens can still be preferentially chosen for equivalent implementations. Other lens designs and fabrications, such as those using conventional aspherical techniques, should also be considered equivalent; this configuration should be self-evident to those skilled in the art and requires no further description.

[0119] A critical evaluation of the optical compression characteristics of the AOE angular range in the superconverter 1108 is required, which involves a trade-off analysis with respect to the following aspects:

[0120] (i) Physical spatial separation between the superconductor and the superlens (e.g., air gap or optical medium), or

[0121] (ii) The focal length of the WLO imaging lens is extended to minimize system thickness while maintaining optimal optical performance.

[0122] Consistent with the other embodiments described, the eye imaging optics unit may be configured with an optical filter to block stray beam interference from non-imaging wavelengths, thereby improving the optical signal-to-noise ratio (SNRo).

[0123] Similarly, consistent with other embodiments, the eye imaging optics and eye illumination optics can be configured for orthogonal polarization imaging to filter out stray beam interference (whether at imaging or non-imaging wavelengths), thereby enhancing SNRo.

[0124] The examples above are merely illustrative explanations of the basic principles and do not constitute exclusive limitations. Different variations with equivalent generalized principles may exist and be implemented.

[0125] Figure 2 The diagram illustrates head-mounted devices (e.g., AI / AR glasses 1201) in some equivalent variant embodiments, consistent with the principles of other embodiments. The labeled components include:

[0126] The glasses are 1202, the predetermined imaging area is 1203, the temples are 1204, the eye imaging optical units are 1205A and 1205B, the illumination optical units are 1206A and 1206B, the nose pad support is 1207, the imaging unit main optical axis is 1200A and 1200B, and the AR lens optical reflective coating is 1208.

[0127] Figure 2 Examples and Figure 1 The difference in this embodiment is that it changes from direct imaging to indirect imaging. Eye imaging optical units 1205A and 1205B capture a near-infrared (NIR) beam emitted from a predetermined imaging region 1203, which is then reflected by an AR lens optical reflective coating 1208 to form an imaging optical path.

[0128] In some embodiments, the AR lens optical reflective coating 1208 may be deposited or laminated on different optical surfaces. In some examples, such optical surfaces may include, but are not limited to, part or all of the surface of an optical element (e.g., an optical waveguide).

[0129] The optical reflective coating 1208 can be applied using thin-film interference deposition technology, exhibiting the following characteristics:

[0130] It has high reflectivity in the near-infrared (NIR) band and is used for indirect imaging of the eye imaging optical units 1205A and 1205B.

[0131] It has high transmittance in the visible light band to enable the human eye to see the world scene optically.

[0132] Furthermore, the AR reflective coating 1208 can reflect a significant portion of non-imaging NIR stray beams from the world-side scene, thereby blocking directly forward-propagating beams (within the imaging field of view AOI) from entering the eye imaging optics. This mechanism enhances the optical signal-to-noise ratio (SNRo) of the imaging system.

[0133] In an alternative embodiment, the AR reflective coating 1208 can be configured as a reflective holographic optical element (rHOE) film, fabricated using interferometric exposure techniques to perform:

[0134] Wavelength and AOI-dependent selectivity reflect NIR beams for indirect imaging while transmitting visible light beams for human eye 1202 optical perspective world-side scenes.

[0135] The diffraction angle design of the reflective holographic optical element rHOE (according to the holographic diffraction grating equation) satisfies the specified angle range [ωis, ωie] for the AOI from the predetermined imaging region 1203.

[0136] For planar AR lenses (e.g., waveguides) combined with diopter-correcting lenses, the AOI / AOE still follows the laws of optical reflection after passing through a folded reflection / refraction path.

[0137] The same principle applies to illumination / imaging optical paths.

[0138] Figure 2 The remaining descriptions can be found in [the original text]. Figure 1 In embodiments based on the equivalence principle, the embodiments include manipulating eye imaging optical units 1205A and 1205B. Metasurface optical elements (super converters).

[0139] This configuration should be self-evident to those skilled in the art and requires no redundant description.

[0140] The present invention also describes a biometric system for retinal illumination and imaging in a head-mounted device. When applied to AR glasses, in such embodiments, the volume constraints of the retinal imaging optics and illumination optics may require dimensions smaller than 2 mm × 2 mm × 2 mm. Clearly, conventional retinal illumination and imaging configurations, such as eyepieces or other conventional optical arrangements, cannot be implemented in such applications.

[0141] Example 1

[0142] This invention describes a bioassay system for retinal illumination and imaging in a head-mounted device. In some embodiments, such as Figure 3a and Figure 3bAs shown, retinal illumination optical units 1301A and 1301B project outgoing illumination beams 1305A and 1305B, which are redirected by the AR lens optical reflective coating 1303. The outgoing beams converge at a predetermined corneal edge and enter the eye.

[0143] After refraction by the anterior structures (cornea and aqueous humor), the light beam forms the entrance pupil at the pupillary plane. Following further refraction by the posterior structures (lens and vitreous humor), the beam diverges to form the retinal incident beams 1304A and 1304B. Upon reaching the retina, the beam interacts with photoreceptor cells, the macula, the optic disc, and choroidal vessels through absorption, diffuse reflection, and scattering, thus forming the retinal reflected beams 1306A and 1306B.

[0144] The retinal reflected beam is refracted by the lens / cornea and exits the pupil through the pupillary plane, becoming the imaging incident beam 1307A, 1307B. The imaging incident beam propagates to the AR lens optical reflective coating 1303, where it is reflected and redirected into the retinal imaging optical units 1302A, 1302B to achieve integrated retinal illumination and imaging optical paths.

[0145] In Example 1, the AR lens optical reflective coating 1303 is redirected to form a functional optical relay for illumination and imaging. The AR lens optical reflective coating 1303 can be configured with a predetermined optical power and can be positioned at predetermined locations in different independent surface areas.

[0146] In some embodiments, the AR lens optical reflective coating 1303 may be deposited or laminated on different optical surfaces. In some examples, such optical surfaces may include, but are not limited to, part or all of the surface of an optical element (e.g., an optical waveguide).

[0147] The optical reflective coating 1303 can be applied using thin-film interference deposition technology, exhibiting high reflectivity in the near-infrared (NIR) band, and is used for redirected illumination / imaging of retinal illumination optical units 1301A, 1301B and retinal imaging optical units 1302A, 1302B.

[0148] Furthermore, the AR reflective coating 1303 can reflect a significant portion of non-imaging NIR stray beams from the world-side scene, thereby blocking directly forward-propagating beams (within the imaging field of view AOI) from entering the retinal imaging optics. This mechanism enhances the optical signal-to-noise ratio (SNRo) of the imaging system.

[0149] In an alternative embodiment, the AR reflective coating 1303 may be configured as a reflective holographic optical element (rHOE) film, fabricated by interferometric exposure techniques to perform wavelength- and AOI-dependent selectivity, reflecting NIR beams used for redirecting illumination / imaging.

[0150] The rHOE's diffraction angle design (based on the holographic diffraction grating equation) satisfies the predetermined illumination output beams 1305A and 1305B and imaging incident beams 1307A and 1307B.

[0151] The retinal illumination optical units 1301A and 1301B project an illumination beam 1305A and 1305B at a predetermined off-axis tilt illumination angle. This beam is reflected by the AR lens optical reflective coating 1303 and converges at the periphery of the cornea. This configuration helps to optimize the suppression of stray beam reflections from the corneal surface.

[0152] A wider illumination beam angle helps to expand the retinal illumination / imaging field of view (FOV), while a narrower illumination beam angle reduces optical reflections from intraocular tissues to enhance contrast in local retinal areas.

[0153] In some embodiments, the retinal illumination / imaging field of view (FOV) can be extended.

[0154] In one embodiment, at least one retinal imaging optical unit is configured according to the application scenario, and the corresponding off-axis layout is mounted in at least one spatial location and orientation. Similarly, in another embodiment, one or more retinal illumination optical units are configured according to the application scenario, and the corresponding off-axis layout is mounted in one or more spatial locations and orientations, and one or a combination thereof is selectively activated by addressable asynchronous switching.

[0155] The pupil plane separates the illumination and imaging optical paths through the optical entrance pupil and exit pupil, and can be configured to have optical conjugate characteristics.

[0156] In some embodiments, the retinal imaging optical unit includes, but is not limited to, an imaging lens and an image sensor.

[0157] In other embodiments, the retinal imaging optical unit is also configured with a composite imaging optical system, which in these embodiments further includes a first (front) and a second (rear) lens, the first (front) and the second (rear) lens being configured as a superlens or a WLO imaging lens, the optical path being arranged between the first and second lenses with a predetermined spatial separation (e.g., an air gap) to achieve volume compression.

[0158] Additionally, in some variant instances, such as Figure 3c As shown, for the sake of simplifying the diagram, the retinal illumination optical unit (1302, reverse optical path) and the retinal imaging illumination optical unit (1301, forward optical path) are described together.

[0159] The illumination source emitted by the retinal illumination optical unit (1302, reverse optical path) passes through the optical projection lens to form a predetermined outgoing light (1305A / 1305B / 1305C).

[0160] The emitted light is projected onto the AR lens optical reflective coating 1303. Redirected by the AR lens optical reflective coating 1303 to form an illuminating emitted beam (1306A / 1306B / 1306C), these beams are refracted by the anterior segment structures (cornea and aqueous humor) to form an entrance pupil at the pupillary plane. After further refraction by the posterior segment structures (lens and vitreous humor), the beam is projected to form a retinal incident beam. Upon reaching the retina, the beam interacts with photoreceptor cells, the macula, the optic disc, and choroidal vessels through absorption, diffuse reflection, and scattering, thereby forming a retinal reflected beam (1307A / 1307B / 1307C).

[0161] The beam of light reflected from the retina is refracted by the lens / cornea and leaves the pupil through the pupillary plane, becoming the incident beam for imaging.

[0162] The imaging incident beam propagates to the AR lens optical reflective coating 1303, and is redirected by the AR lens optical reflective coating 1303 into the retinal imaging optical unit (1301, forward optical path). It is then focused onto the image sensor by the imaging lens, realizing an integrated retinal illumination and imaging optical path.

[0163] Consistent with other examples, the AR lens optical reflective coating 1303 is redirected to form a functional optical relay for illumination and imaging. The AR lens optical reflective coating 1303 can be configured with a predetermined optical power and can be positioned at a predetermined location on the same surface area.

[0164] In some embodiments, for retinal object points / image points, the illumination and imaging optical paths of the retinal imaging optical unit and the retinal illumination optical unit are configured to have optical conjugation characteristics.

[0165] The pupil plane separates the illumination and imaging optical paths through the entrance pupil and the exit pupil, and can be configured to have optical conjugate properties.

[0166] Example 2

[0167] This invention describes a bioassay system for retinal illumination and imaging in a head-mounted device. In some embodiments based on optical path scanning, such as... Figure 4As shown, the retinal illumination optical unit 1402 is collimated into a beam with a predetermined aperture by the optical collimator 1404. This beam is then combined by the optical beam splitter 1403 and directed to the tunable beam deflector 1405, which deflects the reflected beams 1407A / 1407B / 1407C at an angle to the AR lens optical reflective coating 1406. The outgoing beams 1408A / 1408B / 1408C are then redirected via the AR lens optical reflective coating 1406 (refer to the properties of Example 1) to form a predetermined optical scanning path.

[0168] The outgoing light beams 1408A / 1408B / 1408C are refracted by the anterior segment structures (cornea and aqueous humor) to form the entrance pupil at the pupillary plane. After further refraction by the posterior segment structures (lens and vitreous humor), the beam diverges to form the retinal incident beam. Upon reaching the retina, the beam interacts with photoreceptor cells, the macula, the optic disc, and choroidal vessels through absorption, diffuse reflection, and scattering, thus forming the retinal reflected beam.

[0169] The retinal reflected beam is refracted by the lens and cornea to form the imaging incident beam 1409A / 1409B / 1409C, which exits the pupil at the pupillary plane.

[0170] The imaging incident beam propagates to the AR lens optical reflective coating 1406, and is redirected by the AR lens optical reflective coating 1406 to a synchronized tunable beam deflector for angular deflection.

[0171] Finally, the imaging incident beam is split by the optical beam splitter 1403 and redirected into the retinal imaging optical unit 1401, realizing an integrated retinal illumination and imaging optical path.

[0172] In Example 2, the AR lens optical reflective coating 1406 is configured to redirect to form a functional optical relay for illumination and imaging. The AR lens optical reflective coating can be configured with a predetermined optical power and can be positioned at a predetermined location on the same surface area.

[0173] In some embodiments, for retinal object points / image points, the retinal imaging optical unit and the retinal illumination optical unit can be configured to have optical conjugation characteristics by splitting the illumination and imaging optical paths through the coaxial optical beam splitter 1403.

[0174] In other embodiments, the optical beam splitter can be removed, and the retinal imaging optics and retinal illumination optics can be spatially offset to achieve separate imaging and illumination.

[0175] The pupil plane separates the illumination and imaging optical paths through the entrance pupil and the exit pupil, and can be configured to have optical conjugate properties.

[0176] In some embodiments, the optical collimator 1404 may be configured as an optical component including, but not limited to, a wafer-level optical (WLO) collimating lens or a metasurface collimating lens. In some embodiments, the tunable beam steering 1405 may be implemented using angle-tunable optical elements based on digital micromirror devices (DMDs), microelectromechanical systems (MEMS), liquid crystal spatial light modulators (LC-SLMs), or phase change material metasurfaces.

[0177] When the tunable beam steering performs an angular deflection, the corresponding optical scan path follows synchronously. The beam steering can be configured to have a predetermined high-resolution optical scan accuracy, with the angular resolution of each scan step corresponding to the spatial angular resolution of retinal imaging.

[0178] In some embodiments, the retinal imaging optical unit 1401 includes, but is not limited to, an imaging lens and an image sensor.

[0179] In other embodiments, the retinal imaging optical unit is also configured with a compound imaging optical system.

[0180] The composite imaging optical system further includes: a first (front) and a second (rear) lens that can be positioned in front of the tunable beam deflector 1405, the first (front) and the second (rear) lens that can be configured as a superlens or a WLO imaging lens, and the optical path arranged between the first and second lenses with a predetermined spatial separation (e.g., an air gap) to achieve volume compression.

[0181] The retinal illumination optical unit 1402 forms an illumination area of ​​a predetermined light spot on the focal plane of the retina. This illumination area of ​​the predetermined light spot is simultaneously imaged by the coaxial / on-axis retinal imaging optical unit 1401 and focused onto a photoelectric sensor (e.g., a photodiode PD, a single-photon avalanche diode SPAD, etc.), effectively suppressing stray light from off-focal planes from entering the photoelectric sensor and improving imaging contrast.

[0182] Example 3

[0183] This invention relates to a biometric system for retinal illumination and imaging in head-mounted devices. In some waveguide-based embodiments, such as... Figure 6 As shown: The retinal imaging optics and the retinal illumination optics are spatially offset from each other to achieve separate imaging and illumination.

[0184] To simplify the diagram, the retinal illumination optical unit (1602, reverse optical path) and the retinal imaging illumination optical unit (1601, forward optical path) are described together.

[0185] The illumination source emitted by the retinal illumination optical unit (1602, reverse optical path) passes through the optical projection lens to form a predetermined outgoing light.

[0186] The outgoing light enters the optical input coupler (1606, reverse optical path) at a total internal reflection (TIR) ​​angle and is coupled into the optical waveguide 1605.

[0187] The light beam propagates via a TIR to an optical output coupler (1607, reverse optical path), where it is coupled out at a predetermined AOE to form projected illumination beams 1608A / 1608B / 1608C. These beams are refracted by the anterior segment structures (cornea and aqueous humor) to form the entrance pupil at the pupillary plane. After further refraction by the posterior segment structures (lens and vitreous humor), the beam diverges to form the retinal incident beam. Upon reaching the retina, the beam interacts with photoreceptor cells, the macula, the optic disc, and choroidal vessels through absorption, diffuse reflection, and scattering, thus forming the retinal reflected beam.

[0188] The retinal reflected beam is refracted by the lens / cornea and leaves the pupil through the pupillary plane, becoming the imaging incident beam 1609A / 1609B / 1609C.

[0189] The imaging incident beam propagates to the optical input coupler (1607, forward optical path), is coupled into the optical waveguide at a TIR angle, and is transmitted to the optical output coupler (1606, forward optical path) via TIR. There, the imaging incident beam is coupled out and redirected into the retinal imaging optical unit (1601, forward optical path), and focused onto the image sensor through the imaging lens, thus realizing an integrated retinal illumination and imaging optical path.

[0190] In Example 3, a functional optical repeater is formed based on waveguide total internal reflection TIR.

[0191] In some embodiments, the retinal imaging optical unit 1601 includes, but is not limited to, an imaging lens and an image sensor.

[0192] In other embodiments, the retinal imaging optical unit is also configured with a composite imaging optical system, which in these embodiments further includes a first (front) and a second (rear) lens, the first (front) and the second (rear) lens being configured as a superlens or a WLO imaging lens, the optical path being arranged between the first and second lenses with a predetermined spatial separation (e.g., an air gap) to achieve volume compression.

[0193] In some embodiments, for retinal object points / image points, the illumination and imaging optical paths of the retinal imaging optical unit and the retinal illumination optical unit are configured to have optical conjugation characteristics.

[0194] The pupil plane separates the illumination and imaging optical paths through the entrance pupil and the exit pupil, and can be configured to have optical conjugate properties.

[0195] Example 4

[0196] This invention describes a bioassay system for retinal illumination and imaging in a head-mounted device. In some embodiments based on optical path scanning, such as... Figure 7 As shown, the retinal illumination optical unit 1702 is collimated by the optical collimator 1704 into a beam with a predetermined aperture. This beam is then combined by the optical beam splitter 1703 and directed to the tunable beam deflector 1705, which deflects the reflected beams 1709A / 1709B / 1709C at an angle to the optical input coupler (1707, reverse optical path). The beam is coupled into the optical waveguide 1706 at a total internal reflection (TIR) ​​angle and propagates via TIR to the optical output coupler (1708, reverse optical path), where it is coupled out as the output beams 1710A / 1710B / 1710C along a predetermined optical scanning path.

[0197] The outgoing light beam is refracted by the anterior structures (cornea and aqueous humor) to form the entrance pupil at the pupillary plane. After further refraction by the posterior structures (lens and vitreous humor), the beam diverges to form the retinal incident beam. Upon reaching the retina, the beam interacts with photoreceptor cells, the macula, the optic disc, and choroidal vessels through absorption, diffuse reflection, and scattering, thus forming the retinal reflected beam.

[0198] The retinal reflected beam is refracted by the lens and cornea to form the imaging incident beams 1711A / 1711B / 1711C, which exit the pupil at the pupillary plane.

[0199] The imaging incident beam propagates to the optical input coupler (1708, forward optical path), is coupled into the optical waveguide 1706 at a TIR angle, and is transmitted via TIR to the optical output coupler (1707, forward optical path), where it is coupled out to the synchronized tunable beam deflector for angular deflection.

[0200] Finally, the imaging incident beam is split by the optical beam splitter 1703 and redirected into the retinal imaging optical unit 1701, realizing an integrated retinal illumination and imaging optical path.

[0201] In Example 4, a functional optical repeater is formed based on waveguide total internal reflection TIR.

[0202] In some embodiments, for retinal object points / image points, the retinal imaging optical unit and the retinal illumination optical unit can be configured to have optical conjugation characteristics by splitting the illumination and imaging optical paths through the coaxial optical beam splitter 1703.

[0203] 3. In other embodiments, the optical beam splitter can be removed, and the retinal imaging optical unit and the retinal illumination optical unit can be spatially offset from each other to achieve separate imaging and illumination.

[0204] The pupil plane separates the illumination and imaging optical paths through the entrance pupil and the exit pupil, and can be configured to have optical conjugate properties.

[0205] In some embodiments, the optical collimator 1704 may be configured as an optical component including, but not limited to, a wafer-level optical (WLO) collimating lens or a metasurface collimating lens. In some embodiments, the tunable beam steering 1705 may be implemented using angle-tunable optical elements based on digital micromirror devices (DMDs), microelectromechanical systems (MEMS), liquid crystal spatial light modulators (LC-SLMs), or phase change material metasurfaces.

[0206] When the tunable beam steering performs an angular deflection, the corresponding optical scan path follows synchronously. The beam steering can be configured to have a predetermined high-resolution optical scan accuracy, with the angular resolution of each scan step corresponding to the spatial angular resolution of retinal imaging.

[0207] In some embodiments, the retinal imaging optical unit 1701 includes, but is not limited to, an imaging lens and an image sensor.

[0208] In other embodiments, the retinal imaging optical unit is also configured with a compound imaging optical system.

[0209] The composite imaging optical system further includes: a first (front) and a second (rear) lens that can be positioned in front of the tunable beam deflector 1705, the first (front) and the second (rear) lens that can be configured as a superlens or a WLO imaging lens, and the optical path arranged between the first and second lenses with a predetermined spatial separation (e.g., an air gap) to achieve volume compression.

[0210] The retinal illumination optical unit 1702 forms an illumination area of ​​a predetermined light spot on the focal plane of the retina. This illumination area of ​​the predetermined light spot is simultaneously imaged by the coaxial / on-axis retinal imaging optical unit 1701 and focused onto a photoelectric sensor (e.g., a photodiode PD, a single-photon avalanche diode SPAD, etc.), effectively suppressing stray light from off-focal planes from entering the photoelectric sensor and improving imaging contrast.

[0211] In some exemplary embodiments, optical-grade silicon carbide (SiC) material is used as a high-refractive-index substrate for the optical waveguide to reduce the total internal reflection (TIR) ​​critical angle of the waveguide, thereby enhancing the field of view (FOV) angle and coverage area for retinal illumination and imaging.

[0212] Compared to iris imaging, in retinal imaging applications, some embodiments can configure the pixel resolution (PR) to exceed 100 pixels / mm, 200 pixels / mm, or higher to obtain higher resolution retinal images. Accordingly, the modulation transfer function (MTFo) needs to be scaled up accordingly. However, increasing the PR amplifies eye-motion blur artifacts. Even during fixation, involuntary physiological movements, including microsaccades, nystagmus, and drift, degrade image quality.

[0213] Consistent with other embodiments, the eye illumination / imaging optics unit can be configured to define a predetermined pixel offset on the image plane during an illumination / imaging exposure cycle, given a predetermined eye rotation angular velocity. Based on the eye radius Reye and the eye rotation angular velocity Ω, the illumination / imaging exposure cycle TI / TF is constrained to satisfy the predetermined pixel offset MP:

[0214] Reye·Ω / TI < MP / PR

[0215] Where Reye represents the radius of the eyeball, with an average value of 12 mm, and Ω represents the predetermined angular velocity of eyeball rotation, in radians per second (rad / s).

[0216] In some exemplary implementations, the maximum permissible pixel displacement (MP) can be configured to 1 pixel offset precision to maintain subpixel-level motion control precision. This configuration is non-limiting and can be adjusted as needed.

[0217] As described in other embodiments, in some embodiments, the fixation system can be configured to further guide gaze onto a target. For head-mounted devices such as AR glasses, the fixation system can project a predetermined pattern onto the user's eyes via AR display components (e.g., image display source, optical waveguide, and input / output coupler) with a predetermined image focusing distance (i.e., the focusing distance of the virtual image observed in the user's eyes, such as 3 meters, 5 meters, or more). This projection establishes the predetermined pattern as a guided gaze target, wherein the eyes gaze at the pattern in a stable state of retinal focal plane alignment.

[0218] The fixation system can be configured to display real-time feedback of adjustment cues by calculating and analyzing retinal imaging data and / or multiplexed eye-tracking (ET) imaging data. The cues include, but are not limited to: XY-axis misalignment of retinal position, Z-axis movement of retinal distance, degree of pupil dilation, retinal occlusion (caused by eyelashes, eyelids, or blinking), and gaze changes (e.g., pitch / roll / yaw direction).

[0219] In some other embodiments, the fixation system may be further configured to display iris imaging data and / or multiplexed eye-tracking (ET) imaging data in real time.

[0220] In these embodiments, the fixation system is configured by a control unit according to predetermined parameters (e.g., based on individualized optometric parameters) to:

[0221] (a) Real-time rendering of predefined gaze patterns;

[0222] (b) Analyze imaging data of the retina / eye; and

[0223] (c) Generate adjustment cues to guide the gaze of the target through a sequence of actions.

[0224] In other embodiments, the fixation system may additionally incorporate gaze direction modulation to guide the adjustment of the eye's visual axis, thereby enabling a further expansion of the retinal illumination / imaging field of view (FOV) to capture the peripheral retinal region.

[0225] Multi-point fixation systems can guide the focus of illumination and imaging for peripheral retinal vessels.

[0226] In some embodiments, autofocus optics (e.g., MEMS-based, liquid crystal, or fluid refractive optics) can be configured to compensate for refractive errors in a population, typically covering a correction range of approximately ±10D. However, such configurations impose strict limitations on the form factor and weight budget of the AR glasses system.

[0227] In some embodiments of head-mounted devices (such as AR glasses), the retinal imaging optics unit includes individualized corrective prescription lenses (optionally fitted to the eye-facing side of the waveguide) to achieve: refractive correction for different populations, and gaze guidance via a predetermined pattern from the fixation system.

[0228] The retinal object plane is configured to have fixed optical conjugacy relative to the focal plane of the retinal imaging optics unit, thereby eliminating the need for an autofocus component, which is a key advantage for AR glasses with strict size and weight constraints.

[0229] In some embodiments, the configuration of the retinal illumination / imaging optics system for head-mounted devices can be simplified.

[0230] In this example, the retinal illumination / imaging optics unit is configured to achieve wide field of view (wFOI) projection via trans-pars-planar illumination or trans-palpebral illumination, guided by the fixation system and monitored by the eye-tracking system, and the retinal imaging optics unit achieves wide field of view (wFOV) retinal image imaging.

[0231] The retinal illumination optical unit projects a predetermined light beam through the pars plana of the ciliary body or through the eyelid, which penetrates the sclera or eyelid skin biological tissue and diffuses to the retina to form a wide illumination field (wFOI projection). The light is diffused and can uniformly illuminate a wide area of ​​the inner eye. The predetermined light beam can be configured into a pattern that matches the corresponding anatomical structure, such as a planar illumination pattern that matches the surface morphology projection of the pars plana of the ciliary body.

[0232] Upon reaching the retina, the light beam interacts with photoreceptor cells, the macula, the optic disc, and choroidal vessels through absorption, diffuse reflection, and scattering, thus forming a retinal reflected beam. This retinal reflected beam is refracted by the lens / cornea and exits the pupil through the pupillary plane, becoming the imaging incident beam. This beam is then used by the retinal imaging optics unit to achieve wide field-of-view (wFOV) retinal image formation.

[0233] The fixation system is used to actively guide eye fixation (pitch / roll / yaw direction angle) to achieve passive positioning and alignment of the retinal illumination optical unit with the projection onto the ciliary body plana or eyelid area. The eye tracking system is used to monitor and provide feedback on the current eye fixation state in real time, ensuring that the corresponding illumination optical unit is passively positioned and aligned with the optimal projection position on the ciliary body plana or eyelid area.

[0234] Although near-infrared (NIR) light has higher reflectivity and deeper tissue penetration than visible light, penetrating the retinal pigment epithelium and reaching the choroid, it provides clear imaging of deep structures such as the outer retina, RPE, and choroid. Furthermore, it allows fixation systems to operate without mydriasis at these wavelengths and is less affected by media such as lens opacity. However, as those skilled in the art know, due to the differential absorption of photoreceptors, retinal arterioles / venules, and the macula / optic disc, it offers high resolution for superficial blood vessels (dependent on hemoglobin absorption) and nerve fiber layers; it provides color morphological information consistent with natural vision, and the visible spectrum provides higher background contrast.

[0235] Therefore, some embodiments can operate in the visible-NIR wavelength range to configure multispectral illumination and imaging.

[0236] Consistent with the other embodiments described, the retinal imaging optics unit and the retinal illumination optics unit are configured in orthogonal polarization states for illumination and imaging, thereby eliminating imaging artifacts caused by corneal surface reflection and intraocular backscattering.

[0237] Orthogonal polarization states enhance the optical signal-to-noise ratio (SNRo).

[0238] Furthermore, and in conjunction with the description of other embodiments below, and in accordance with the general principles, the polarization direction of linearly polarized light (0 / 45 / 90 / 135°) exhibits a complex angular orientation dependence on local structures of ocular biological tissues (such as retinal nerve fibers), resulting in different depolarization effects. In contrast, circularly polarized light (LCP / RCP) can minimize the effects of angular orientation dependence.

[0239] In some embodiments, illumination / imaging with parallel and orthogonal polarization states can capture reflection or scattering information of ocular biological tissues at different wavelengths and depths. For example, short-wavelength green and blue light in the spectrum can be partially retained (linear polarization state) or chiral inverted (circular polarization state) after reflection (specular reflection / diffuse reflection) from the surface or shallow layer (outer segment of photoreceptor) of the retina. Long-wavelength red and near-infrared light can penetrate deeper into the inner layer of the retina (retinal pigment epithelium and choroid) and be backscattered to form a depolarized state.

[0240] Therefore, the combination of parallel polarization and orthogonal polarization in illumination / imaging configurations can capture complete polarization state biomarker information to generate characteristic high-contrast images for physiological health status analysis.

[0241] Furthermore, some embodiments can be configured with an on-chip photonic integrated circuit (PIC) interferometer, which is configured for single-axis scanning in spectral domain SD or swept-frequency source SS mode, for biometric determination of eye depth structural information, such as anterior and posterior corneal thickness, aqueous humor depth, lens thickness, retinal and choroidal thickness, axial length, etc.

[0242] Next, several variant embodiments based on polarized eye illumination / imaging optics are introduced for dynamic qualitative / quantitative monitoring and analysis of physiological states, consistent with the descriptions of other embodiments.

[0243] In some embodiments, the bioassay system includes:

[0244] The eye illumination optics unit is configured to emit light having at least one polarization state toward the eye; the eye imaging optics unit is configured to capture an image using an image sensor sensitive to at least one corresponding polarization state; and the control unit is configured to generate at least one combination of identical and orthogonal polarization states, synchronize timing, and process polarization intensity data from the image.

[0245] According to some implementations, the polarization intensity data is configured with at least one of corneal polarization interference intensity pattern mode and / or scleral polarization scattering intensity pattern mode as a cross-reference feature characterizing the physiological state of the eye.

[0246] In some embodiments, the polarized eye illumination / imaging optics unit is configured with a linear / chiral circularly polarized sensitive optical metamaterial / structure (e.g., a helical chiral circularly polarized sensitive structure / metamaterial) or a metasurface polarization grating, having the following characteristics: at a wavelength of 940 nm, the circularly polarized metasurface has a circular dichroism (CD) > 80%, 90%, or higher, an extinction ratio > 100:1, 1000:1, or higher; and a transmittance > 50%, 60%, 70%, 80%, 90%, or higher; at a wavelength of 940 nm, the linearly polarized metasurface has an extinction ratio > 100:1, 1000:1, or higher; and a transmittance > 50%, 60%, 70%, 80%, 90%, or higher.

[0247] In some embodiments, silicon-based high-performance, all-dielectric pixelated, all-Stokes polarized metasurfaces in the near-infrared band are compatible with existing CMOS semiconductor industry technologies. Circularly polarized (CP) metasurfaces with high circular dichroism (CD) are realized using simple two-dimensional chiral structures, which can be easily integrated with linearly polarized metasurfaces on a chip system. Furthermore, the dielectric material exhibits higher transmittance than metallic materials with inherent absorption. In some embodiments, for the pixelated all-Stokes polarized metasurface, each pixel has four spatially distributed polarization structures. The linearly polarized (LP) structures are configured with nanowire gratings oriented in three different directions to transmit linearly polarized light, with their electric field vectors oriented at 0°, 90°, and 45° relative to the x-axis, respectively. The LP structures transmit TM-polarized light with an electric field direction perpendicular to the grating grooves, while blocking the transmission of TE-polarized light with an electric field direction parallel to the grating grooves. The CP structures are configured with a special parity-symmetric planar pattern that transmits right-hand circularly polarized (RCP) light and blocks left-hand circularly polarized (LCP) light, and vice versa.

[0248] In other embodiments, the pixelated polarization direction of the polarized eye illumination / imaging optics unit can be stabilized by an etched metasurface grating structure with subwavelength period and etching depth. This subwavelength metasurface structure can be mass-produced at high throughput and low cost using nanoimprint lithography.

[0249] Another alternative example of a polarized eye illumination / imaging optics unit can be configured, for instance, based on a metasurface diffraction polarization grating. See Matrix Fourier optics enables a compact full-Stokespolarization camera, Science, 5 Jul 2019, Vol 365, Issue 6448 DOI: 10.1126 / science.aax1839.

[0250] Figure 8 (Right) Shows a partial SEM (scanning electron microscope) image of a subwavelength metasurface grating structure with 0° directional polarization.

[0251] In some embodiments, a phase retarder is stacked on a metasurface grating linear polarizer (LP) layer, wherein the retarder comprises nanopillars (metal / dielectric superatoms) having a predetermined phase delay along orthogonal directions. The fast / slow axes of the retarder are configured at +45° / −45° relative to the transmission axis of the metasurface grating to produce right-handed / left-handed circular polarization (RCP / LCP).

[0252] In some embodiments, multi-polarization state metasurface gratings or linear / chiral circularly polarized sensitive optical metamaterials can be stacked on top of the image sensor layer.

[0253] In some embodiments, the polarized eye illumination / imaging optics unit can be configured using tunable liquid crystal (LC) / phase change materials to enable real-time, independently controllable polarization state switching. This tunability enhances polarization state resolution.

[0254] Polarized eye illumination / imaging systems (especially RCP / LCP configurations) offer:

[0255] (a) Ambient stray light suppression - Blocks complex ambient light, including: direct incident light (AOI) and primary / secondary indirect reflections;

[0256] (b) Reduced ocular surface reflexes - Reduce interference from ocular surface contaminants (tears, secretions) and periocular skin reflexes (cosmetics, oils).

[0257] This makes it possible to acquire high-quality polarization intensity images in eye image sequences.

[0258] Since the natural environment exhibits negligible circular polarization (CP) in most cases, some embodiments can employ an RCP / LCP configuration compared to linear polarization / partial linear polarization (LP) to: effectively eliminate ambient stray light in imaging; and improve the optical signal-to-noise ratio (SNRo) by more than 20 dB in testing.

[0259] Example 1: The control unit is configured with a polarized eye imaging optical unit to form a 2×2 pixelated multi-polarization imaging array with orientations of 0°+90°+45°+135°. Accordingly, the polarized eye illumination optical unit is configured to operate at any one of 0° / 90°, 45° / 135°, or any combination thereof.

[0260] Example 2

[0261] The control unit configures a polarized eye imaging optical unit to form a 2×2 pixelated fully polarized imaging array with directions of 0°+90°+45° / 135°+RCP / LCP. Accordingly, the polarized eye illumination optical unit is configured to operate at any one or any combination of 0° / 90°, 45° / 135°, and RCP / LCP.

[0262] Example 3

[0263] The control unit is configured with a polarized eye illumination optics unit to form a 2×2 switchable multi-polarization illumination with directions of 0°+90°+45°+135°. Accordingly, the polarized eye imaging optics unit is configured to perform pixelated polarization imaging in any of the 0° / 90° or 45° / 135° polarization states.

[0264] Example 4

[0265] The control unit is configured with a polarized eye illumination optics unit to form a 2×2 switchable fully polarized illumination with directions of 0°+90°+45° / 135°+RCP / LCP. Accordingly, the polarized eye imaging optics unit is configured to perform pixelated polarized imaging in any of the 0° / 90°, 45° / 135°, or RCP / LCP polarization states.

[0266] Example 5

[0267] The control unit is configured with a polarized eye illumination optics unit to form illumination with RCP+LCP polarization states. Correspondingly, the polarized eye imaging optics unit is configured for pixelated multi-polarization imaging at 0°+90°+45°+135°.

[0268] Example 6

[0269] The control unit is configured with a polarized eye illumination optics unit to form illumination with polarization states of 0°+90°+45°+135°. Correspondingly, a polarized eye imaging optics unit is configured for pixelated multi-polarization imaging in RCP+LCP.

[0270] In some embodiments, the control unit is configured as follows:

[0271] (i) Synchronize the following timing sequence:

[0272] The optical radiation of the polarized eye illumination optical unit, and

[0273] Exposure (integration) period of polarized eye imaging optical unit.

[0274] (ii) During illumination-imaging operations, establish addressable coded associations for each combination of parallel (identical) and orthogonal polarization states; and

[0275] (iii) Selectively activate / deactivate specific polarization states by asynchronous switching.

[0276] The control unit receives digital polarization intensity data (pixelated image) from the image sensor, which is generated by at least one configured combination of parallel (identical) and orthogonal polarization states.

[0277] In some embodiments, the polarization intensity data (pixelated image) for illumination and imaging is generated by a combination of parallel (identical, denoted as p) and orthogonal (denoted as s) polarization states, specifically defined as follows:

[0278] 1. Set of independent polarization states:

[0279] {0°, 90°, 45°, 135°, RCP, LCP}

[0280] 2. The set of orthogonal polarization states, s:

[0281] {(0°,90°), (45°,135°), (RCP,LCP)}

[0282] 3. The set p of parallel (identical) polarization states:

[0283] {(0°,0°), (45°,45°), (RCP,RCP)} or equivalently: {(90°,90°), (135°,135°),(LCP,LCP)}

[0284] 4. Parallel + Orthogonal combination set p + s:

[0285] {(0°,0°)+(0°,90°), (45°,45°)+(45°,135°), (RCP,RCP)+(RCP,LCP)}; or equivalently: {(90°,90°)+(0°,90°),(135°,135°)+(45°,135°), (LCP,LCP)+(RCP,LCP)};

[0286] Polarization intensity data (pixelated image) corresponding to the following:

[0287] The set of parallel (identical) polarization states p is denoted as Ip;

[0288] The set of orthogonal polarization state combinations s is denoted as Is.

[0289] In different embodiments, any subset of the above-described combination set can be implemented.

[0290] The above configurations of parallel (identical) and orthogonal polarization states are for illustrative purposes only and are not intended to be exclusive or restrictive. Equivalent variants based on the same fundamental principles can be implemented and carried out.

[0291] Birefringence is a core aspect of the cornea's optical properties, stemming from the highly ordered arrangement of collagen fibers and the unique characteristics of the surrounding biological matrix.

[0292] The layered structure of corneal collagen fibers is the primary source of optical anisotropy and birefringence. Their radial symmetry and circumferential arrangement directly contribute to the observed biological birefringence effect.

[0293] The optical mechanisms of corneal birefringence include:

[0294] 1. The curvature of the corneal surface causes angular rotation and phase delay of incident light;

[0295] 2. Phase delay caused by the circumferential angular orientation of birefringent collagen fibers within the cornea.

[0296] The cornea is a uniaxial birefringent medium, exhibiting refractive index differences along orthogonal polarization axes.

[0297] Light incident parallel or perpendicular to the corneal surface is unaffected, while light incident at an angle undergoes polarization axis rotation and phase retardation. This is essentially equivalent to changing the angular relationship between the polarization direction and the fast / slow axis of the cornea.

[0298] In some embodiments, when the transmission axes of the polarized eye illumination optics unit and the eye imaging optics unit are configured to be parallel (identical) or orthogonal, the birefringence of the corneal biological tissue (determined by the birefringence index) is... The polarization interference effect is determined by optical parameters such as wavelength and corneal thickness.

[0299] This effect is characterized by interference intensity between parallel (identical) and orthogonal polarization states, exhibiting approximately symmetrical periodicity and presenting as four phase-reversed maxima and minima. These properties are reflected in the characteristics of patterned modes, such as... Figure 5 As shown.

[0300] The combination of parallel (identical) and orthogonal polarization states configured as p + s is: (0, 0) + (0, 90).

[0301] Relative to the parallel (identical) polarization state combination subset p=(0,0) in the illumination / imaging configuration, regions 151A, 151B, 151C, and 151D exhibit destructive interference within the patterned modes, while the remaining regions exhibit constructive interference.

[0302] Relative to the orthogonal polarization state combination subset s=(0,90) in the illumination / imaging configuration, regions 152A, 152B, 152C, and 152D exhibit constructive interference within the patterned modes, while the remaining regions exhibit destructive interference.

[0303] For a fixed AOI incident light, the corneal polarization interference intensity pattern mode of the orthogonal polarization state combination configuration (0, 0) + (0, 90) is characterized by the individual corneal birefringence fast axis orientation angle and corneal birefringence phase retardation characteristics.

[0304] The corneal polarization interference intensity pattern mode exhibiting polarity reversal between parallel (identical) and orthogonal polarization states can be characterized as a cross-reference feature and can serve as a corneal feature of the eye.

[0305] Despite the non-uniform variations in corneal thickness and inter-individual biological differences, the cross-reference characteristics of the corneal polarization interference intensity pattern corresponding to the birefringence effect remain consistent within the same body.

[0306] In some other embodiments, when applied to long-term health monitoring of an individual, dynamic qualitative / quantitative analysis of the eye's physiological state may also include the scleral region. Within the scleral region, collagen and elastic fibers, through their disordered anisotropic distribution and vascular absorption properties, provide surface scattering of incident light from the polarized eye illumination optics unit. The scattered light can be detected by the polarized eye imaging optics unit.

[0307] The combination of parallel (identical) and orthogonal polarization states configured as p + s is: (0,0) + (0,90).

[0308] The imaging pattern mode displays a scattering pattern with a 0° polarization (parallel) region relative to the parallel (same) polarization state combination subset p=(0,0) in the illumination / imaging configuration, denoted as 151E / 151F.

[0309] The imaging pattern mode displays a scattering pattern with a 90° polarization (orthogonal) region relative to the orthogonal polarization state combination subset s=(0,90) in the illumination / imaging configuration, denoted as 152E / 152F.

[0310] The scleral polarization scattering intensity pattern mode exhibiting polarity reversal between parallel (identical) and orthogonal polarization states can be characterized as a cross-reference feature and can serve as a feature of the sclera of the eye.

[0311] Various combined illumination-imaging configurations using parallel (identical) and orthogonal polarization states are employed to generate corresponding imaging pattern modes that reflect one or both of the following:

[0312] (i) Changes in corneal polarization interference intensity, and

[0313] (ii) Variations in scleral polarization scattering intensity provide cross-reference features with higher accuracy and stability. In various embodiments, the aforementioned cross-reference feature data can be implemented in any subset of the combined configuration set.

[0314] For more examples of combined configurations, please refer to Figure 9 The figure above shows the corneal polarization interference intensity pattern mode of LCP+LCP. With a fixed AOI incident light, it is characterized only by the individual corneal birefringence phase retardation characteristics, and has no correlation with the corneal birefringence fast axis orientation angle characteristics.

[0315] The figure below shows the corneal polarization interference intensity pattern mode of 0(LP)+LCP, characterized by individual corneal birefringence phase retardation and corneal birefringence fast axis orientation angle characteristics under fixed AOI incident light.

[0316] From an information theory perspective, cross-reference feature encoding of polarity-reversed channels (parallel and orthogonal polarization states) can maximize entropy, while simultaneously suppressing noise (optical noise, electrical noise, etc.), eliminating interference (motion artifacts, random polarized light, etc.), and enhancing the signal of patterned modes (corneal polarization interference intensity and / or scleral polarization scattering intensity).

[0317] The control unit is pre-trained with a lightweight machine learning / deep learning model (e.g., CNN, DNN, RNN, GNN, ViT) and uses a high-dimensional mapped cross-reference feature dataset configured with at least one or more combinations of polarization states, including corneal polarization interference intensity patterns and / or scleral polarization scattering intensity patterns, to perform end-to-end inference to predict dynamic qualitative / quantitative monitoring and analysis of ocular physiological states.

[0318] Machine learning / deep learning models can learn intrinsic pattern modes of high-dimensional mappings that characterize the physiological state of the eye by pre-training on cross-reference feature datasets of corneal polarization interference intensity patterns and / or scleral polarization scattering intensity patterns.

[0319] In some embodiments, data preparation generates a high-dimensional mapping dataset containing cross-reference features extracted from at least one or more combinations of parallel (identical) and orthogonal polarization states and their corresponding physiological states. The control unit, after pre-training a lightweight machine learning / deep learning model by inputting this high-dimensional mapping dataset, performs end-to-end predictive inference, outputting dynamic qualitative / quantitative monitoring and analysis of the eye's physiological state.

[0320] In some embodiments, the cross-reference features of the corneal polarization interference intensity variation imaging pattern and / or the scleral polarization scattering intensity variation imaging pattern can be defined based on artificial feature extraction, such as differential features (Ip-Is) or contrast features, including but not limited to Is / (Ip+Is) and (Ip-Is) / (Ip+Is).

[0321] In some embodiments, the cross-reference features of corneal polarization interference intensity variation imaging patterns and / or scleral polarization scattering intensity variation imaging patterns can be combined with a dual-channel or multi-channel feature fusion unit in a deep learning model, wherein Ip and Is are respectively input to the feature fusion unit to perform autonomous high-dimensional feature extraction.

[0322] Transformer models excel at modeling long-range dependencies, while feature fusion combines local details and multi-layered visual information. The effective combination of these two technologies endows the model with both global understanding and local perception capabilities, significantly improving performance and generalization ability while reducing computational costs.

[0323] Transformer learns the feature dependencies within image channels through a channel self-attention mechanism, and combines multi-scale feature extraction and fusion units to effectively process global information with higher computational efficiency.

[0324] In some embodiments, the deep learning model is configured to incorporate a dual-channel / multi-channel feature decoupling block within a Transformer-based ViT backbone network to directly decouple the cross-reference features of Ip and Is. This feature decoupling block decouples the cross-reference features of Ip and Is through dual-channel / multi-channel processing and then globally fuses them with the original features, thereby enhancing the multi-scale spatial feature representation. A cross-attention mechanism is utilized to model the spatial relationships of the cross-reference features, and this block performs spatial and cross-channel information decoupling through a convolutional feedforward network.

[0325] In some embodiments, a bidirectional spatiotemporal convolutional network architecture can be configured to extract spatiotemporal features from both forward and reverse time series simultaneously, while leveraging a self-attention mechanism to highlight key features based on the extracted spatiotemporal features.

[0326] In other embodiments, a temporal difference Mamba (TD-Mamba) block can be combined with a dual-stream SlowFast architecture, which efficiently processes short-term and long-term temporal features to enhance the detection accuracy of dynamic changes in cross-reference features.

[0327] The above cross-reference feature extraction configuration is provided only as an illustrative example of the operating principle and should not be construed as exclusive or restrictive. Variations embodying the equivalent principle can be extended and implemented without departing from the scope of the invention.

[0328] Since Ip and Is images themselves include the periocular region, the corneal polarization interference intensity pattern occurs specifically in the transparent corneal region, while its corresponding characterization is manifested in the anatomically posterior iris region.

[0329] In some exemplary embodiments, the region of interest (ROI) of a corneal polarization interference intensity pattern can be defined as an iris region, wherein a dataset of polarization combinations of at least one or more corneal interference pattern ROIs is used during deep learning model training or inference.

[0330] In some embodiments, the corneal polarization interference intensity pattern can be localized within a region of interest (ROI), for example by detecting key points of the iris ROI from an Is+Ip composite image while excluding invalid occlusions (e.g., eyelashes, eyelids, blink artifacts). The deep learning model can perform occlusion masking annotation during training and / or inference to suppress interference. In a further embodiment, normalization of the ROI can compensate for accuracy errors caused by pupil dilation / contraction.

[0331] In some embodiments, the scleral polarization scattering intensity pattern can be located within the scleral region of interest (ROI), for example by detecting key points of the scleral ROI from the Is+Ip composite image.

[0332] The exemplary deep learning model configuration described above, driven by cross-reference feature data from corneal polarization interference intensity patterns and / or scleral polarization scattering intensity patterns exhibiting polarity reversal between parallel (identical) and orthogonal polarization states, is provided only as an illustrative embodiment of the basic principles and should not be construed as limiting or exclusive. Various alternative embodiments embodying the equivalent principles can be generalized and practiced without departing from the scope of the invention.

[0333] In some embodiments, qualitative / quantitative monitoring based on corneal polarization interference intensity patterns and / or scleral polarization scattering intensity patterns can enable longitudinal comparison of changes in individual health status data.

[0334] In long-term health monitoring applications, the system is initialized by creating a historical health record file for each individual.

[0335] When an individual's ocular health changes, such as keratoconus progression, intraocular pressure fluctuations, blood pressure changes, hemodynamic perfusion abnormalities, or changes in aqueous humor glucose optical rotation, these alterations can lead to corresponding changes in corneal curvature, birefringence, and scleral scattering properties. These changes are reflected in the cross-reference features of the corneal polarization interference intensity pattern and / or the scleral polarization scattering intensity pattern. By comparing with historical health records, a trained deep learning model can perform dynamic qualitative / quantitative monitoring and analysis and generate diagnostic feedback alerts.

[0336] As described in other embodiments, in some embodiments, the fixation system is further configured to guide gaze onto a target. For head-mounted devices such as AR glasses, the fixation system can project a predetermined pattern onto the user's eyes via AR display components (e.g., image display source, optical waveguide, and input / output coupler) with a predetermined focusing image distance (i.e., the focusing distance of the virtual image in the user's eyes, such as 3 meters, 5 meters, or infinity). This projection establishes the predetermined pattern as a guide gaze target, wherein the eyes fixate on the pattern with a stable visual / optical axis.

[0337] The fixation system can be configured to display real-time feedback on adjustment cues by calculating and analyzing iris imaging data and / or multiplexed eye-tracking (ET) imaging data. The cues include, but are not limited to: XY-axis offset alignment of iris position, Z-axis movement of iris distance, degree of pupil dilation, iris occlusion (e.g., caused by eyelashes, eyelids, or blinking), and gaze changes (e.g., pitch / roll / yaw).

[0338] In some other embodiments, the fixation system may be further configured to display iris imaging data and / or multiplexed eye-tracking (ET) imaging data in real time.

[0339] In these embodiments, the fixation system is configured by a control unit according to predetermined parameters (e.g., based on individualized refraction parameters) to:

[0340] (a) Real-time rendering of predefined gaze patterns;

[0341] (b) Analyze imaging data of the iris and / or eye; and

[0342] (c) Generate adjustment cues throughout the operation sequence to guide gaze at the target.

[0343] Consistent with other embodiments, the polarized eye illumination / imaging optics unit can be configured to define a predetermined pixel offset on the image plane during illumination / imaging exposure under a predetermined eye rotation angular velocity. Based on the eye radius Reye and the eye rotation angular velocity Ω, the illumination / imaging exposure period TI / TF is constrained to satisfy the predetermined pixel offset MP.

[0344] Consistent with other embodiments, the polarized eye illumination / imaging optics unit can also be configured for multispectral illumination and imaging in the visible-near-infrared (VIS-NIR) wavelength range. In such embodiments, the polarized eye illumination optics unit can be configured to emit multi-wavelength channel illumination across the VIS-NIR spectrum, while the polarized eye imaging optics unit can include a corresponding pixelated multi-wavelength channel filter. This filter can be stacked and integrated on top of the pixelated polarizer layer of the image sensor to extract pixelated multi-wavelength channel information, thereby generating multi-polarization, multi-wavelength channel pixelated imaging data.

[0345] Taking wavelengths of 660 nm and 940 nm as examples, a pixelated 4-channel configuration with polarization states of 0 degrees and 90 degrees forms the following channels:

[0346] - 660 nm wavelength channel with 0-degree polarization;

[0347] - A 660 nm wavelength channel with 90-degree polarization;

[0348] - 940 nm wavelength channel with 0-degree polarization;

[0349] - 940 nm wavelength channel with 90-degree polarization.

[0350] Longer wavelength bands exhibit enhanced penetration into biological tissues such as the sclera, for example, 1050 nm near-infrared (NIR) radiation.

[0351] In some implementations, the image sensor can be configured in a pixel-merging / subsampling mode, where pixels in the same polarization channel are combined to enhance sensitivity, reduce power consumption, or increase frame rate.

[0352] In other embodiments, metasurface optical elements can be configured as metasurface pixel-level polarization-focusing spectral routers for image sensors, performing optical modulation function multiplexing on incident light in both the pixel channel wavelength and polarization dimensions, including: predetermined polarization state manipulation, incident principal ray angle CRA focusing, and predetermined wavelength-sensitive pixel channel selective routing. This optimizes pixel channel crosstalk and light utilization, and can replace traditional wavelength filters (CFAs) and / or microlenses and / or on-chip polarizers. Retaining the on-chip polarizer can enhance the extinction ratio.

[0353] The metasurface pixel-level polarization focusing spectral router, which multiplexes pixel-channel optical modulation functions in response to the incident light field, has the following characteristics:

[0354]

[0355] The multiplexing characteristic of pixel channel optical modulation function is characterized by the decoupling of phase modulation term and polarization modulation term.

[0356] in:

[0357] Φ(x, y) is the phase modulation term; j∈[1, N] N is the number of channels in the wavelength dimension; i∈[1, M] M is the number of channels in the polarization dimension; k=2π / λj; φ represents the focal center position of the corresponding dimensional channel; φ represents the phase compensation amount of the corresponding dimensional channel; in some instances, it responds to the incident principal beam angle CRA corresponding to different pixel channels. f is the focal length of the metasurface pixel-level polarization focusing spectral router; the metasurface pixel-level polarization focusing spectral router is composed of N*M meta-atoms of wavelength and polarization dimensions forming a unit cell.

[0358] like Figure 10a As shown, 1902 / 1903 / 1904 / 1905 are the image sensor sub-pixels corresponding to the wavelength dimension channel and polarization dimension channel of the metasurface pixel-level polarization focusing spectral router 1901, which together constitute a macro-pixel. The sub-pixel layout photonic sensor performs photoelectric conversion and can be configured with pixelated full front-side deep trench isolation (FDTI / DTI) to further improve optical and electrical pixel channel crosstalk and improve full-well capacity (FWC).

[0359] In some embodiments, the image sensor may be configured as a quantum dot (QD) image sensor or a silicon-based back-illuminated (BSI) CMOS image sensor. In some embodiments, the image sensor may also be configured as a dynamic event image sensor that asynchronously detects pixel-level brightness change events as a response output.

[0360] In some embodiments, one or more photoelectric sensors, such as CMOS image sensors, defocused image sensors, light field sensors, or single-photon avalanche diodes (SPADs), and / or, in some embodiments, non-imaging sensors, such as self-mixing interferometry (SMI) sensors. In some embodiments, the combined VCSEL / SMI photonic integrated circuit (PIC) can be used simultaneously as an illumination source and an eye-tracking sensor to detect the direction and velocity of eye movement via Doppler frequency shift.

[0361] Figure 10a The 4-pixel channels are represented as arranged in a 1D form, but can also be arranged as follows: Figure 10b The equivalent 4-pixel channels are arranged in a 2D form.

[0362]

[0363] Where J(x, y) is the polarization modulation term, which can be decomposed into two sets of orthogonal polarization eigenvalues ​​using matrix Fourier optics. Incident unpolarized light can be decomposed into a pair of incoherent superpositions of orthogonal polarization states; F -1 For the Fourier inverse transform, Ji(k) x ,k y ) is the Jones matrix of the target polarization state on the predefined Poincaré sphere (focal plane) for the corresponding pixel channel, which is determined by the corresponding eigenstate Jones vector |α(k) x ,k y The outer product of the vectors of its orthogonal states (Jones) is constituted; Ji(k) x ,k y ) is a unitary matrix, Ji(k) x ,k y ) † Ji(k x ,k y ) = I identity matrix; where † is the conjugate transpose.

[0364]

[0365]

[0366]

[0367] Where χ is the elliptic angle corresponding to the target polarization state; ψ is the orientation angle corresponding to the target polarization state; J(x,y) is composed of a subwavelength nano-optical phase retarder made of birefringent dielectric nanopillars. The Jones matrix J(x,y) with a local unit cell metasurface can be well approximated as a linear birefringent waveplate.

[0368]

[0369] Where J(x, y) is a unitary matrix, J(x, y) † J(x, y) = I, the identity matrix; J(x, y) represents the Jones matrix of the metasurface for an incident light field, fully describing the transformation of the polarization and phase of the light wave at each point (x, y) of a birefringent optical element. The metasurface achieves the construction of a matrix grating by independently designing three spatially varying parameters: φx(x, y): phase modulation in the x-direction; φy(x, y): phase modulation in the y-direction; θ(x, y): rotation angle of the optical axis, through tuning the length, width, and orientation angle of the dielectric nanopillars.

[0370] In other instances, J(x, y) can be configured as the Jones matrix of a metasurface in a unit lattice (unit cell) system with multiple superatomic structures. The metasurface Jones matrix can be decoupled and represented as: the number of n types of superatoms, and the linear combination of the Jones matrix Jn(x, y) of each superatom, which is the transfer matrix.

[0371] J(x, y)=∑Jn(x, y)

[0372] A mapping relationship is generated between the metasurface structure parameters (size, rotation angle, number of superatoms) of the multi-atom unit lattice system and the target polarization state on the corresponding Poincaré spherical coordinates (elevation angle, azimuth angle, radius).

[0373] For the incident light field Ein(x,y) on the metasurface pixel-level polarization focusing spectral router, after multiplexing via pixel channel optical modulation, the corresponding output light field Eout(x,y) is:

[0374]

[0375]

[0376] (x, y) represent the coordinates on the metasurface pixel-level polarization focusing spectral router; (x', y') represent the coordinates on the image sensor pixel channel; F represents the Fourier transform; F -1 denoted as inverse Fourier transform; P is the amplitude pupil function of the metasurface pixel-level polarization focusing spectral router; H represents the spatial frequency transfer function of the light wave propagation distance f; u and v are spatial frequency coordinates.

[0377] In some embodiments, a metasurface pixel-level polarization focusing router based on metasurface optical elements for image sensors can be configured to perform polarization dimension optical modulation function multiplexing on incident light, including: predetermined polarization state manipulation and pixel channel selective routing for incident principal ray angle CRA focusing, thereby optimizing pixel channel crosstalk and light utilization. It can replace microlenses and / or on-chip polarizers, while retaining on-chip polarizers can enhance the extinction ratio.

[0378] In some embodiments, a metasurface pixel-level spectral focusing router based on metasurface optical elements for image sensors can be simplified to perform wavelength-dimensional optical modulation function multiplexing of the incident light, including: pixel channel selective routing with predetermined spectral wavelength sensitivity and incident principal ray angle CRA focusing, thereby optimizing pixel channel crosstalk and light utilization, and can replace traditional wavelength filter CFA and / or microlens.

[0379] In these embodiments, metasurface optical element layers can be fabricated using CMOS processes at process nodes such as 40nm or below, and image sensor integration can be achieved using wafer-level bonding technology.

[0380] Furthermore, in some embodiments, the eye illumination optics unit and the eye imaging optics unit can also be configured with monolayer dielectric metasurface optical elements for optical modulation multiplexing to generate and detect / image (Metrology) with orbital angular momentum (OAM) modes. The decoupled characterization of the OAM mode modulation terms is as follows:

[0381]

[0382] l represents the topological charge number, and the azimuth angle ψ(x, y) = arctan(y / x) possesses optical properties carrying the orbital angular momentum mode, exhibiting higher permeability in biological tissues. In some instances, the OAM mode can be configured with l > 10. Higher orbital angular momentum (larger topological charge) results in greater permeability, leading to greater scattering depth and feature contrast in biological tissues.

[0383] Metasurface optical elements, through subwavelength nanostructure arrays, enable arbitrary manipulation of light waves on a single-layer plane. In some examples, orbital angular momentum (OAM) mode modulation can be configured as an integrated vector vortex beam (VVB). Based on geometric phase (Pancharatnam-Berry phase) modulation, by rotating anisotropic nanostructures, opposite additional phases are introduced to left- and right-hand circularly polarized light, directly outputting circularly polarized vortex light carrying OAM. For linearly polarized light (decomposed into a superposition of left- and right-hand circularly polarized light), a vector vortex beam is output as a coherent superposition of two orthogonal left- and right-hand circularly polarized vortex beams.

[0384] In other instances, integrated vector vortex beams can also combine hybrid phase modulation of geometric and propagation phases. By changing the dimensions (such as length and width) of the nanostructures, the effective refractive index can be modulated, thereby controlling the propagation phase. Combining propagation and geometric phases enables independent phase modulation of orthogonally polarized beams, allowing for greater design freedom.

[0385] Corresponding to specific wavelengths / polarization states and orbital angular momentum (OAM) modes, biological tissues exhibit specific media absorption / scattering photon propagation path behaviors, resulting in distinguishable bio-information responses.

[0386] In this embodiment of the invention, the eye illumination optical unit and the eye imaging optical unit can be configured to perform optical modulation functions based on metasurface optical elements to perform orbital angular momentum (OAM) mode, wavelength dimension, and polarization dimension optical modulation on incident light in any combination.

[0387] The examples above are merely illustrative explanations of the basic principles and do not constitute exclusive limitations. Different variations with equivalent generalized principles may exist and be implemented.

[0388] Although the eye illumination optical unit in the embodiments of the present invention exemplarily uses an incoherent broadband light-emitting diode (LED) illumination source, which has advantages such as low cost, high safety and no need for laser protection, other embodiments may alternatively use a coherent narrowband illumination source such as a superluminescent diode (SLD) or VCSEL, and implement it in conjunction with homogenizing and / or structured light devices.

[0389] In some instances, the eye illumination optical unit can be configured as a broadband LED illumination source (e.g., FWHM 40-60nm), a polarization beam shaping OAM mode modulator based on metasurface optical elements, which performs optical modulation functions of predetermined polarization states (0 / 45 / 90 / 135 linear polarization / left / right circular polarization), beam shaping (homogenization and / or structured light) and OAM modes (topological charge l) on the incident light of the illumination source in any combination.

[0390] In these examples, as described above, the optical modulation multiplexing of metasurface optical elements can also combine hybrid phase modulation of the geometric phase and the propagation phase. By changing the dimensions of the nanostructure (such as length and width), the effective refractive index can be modulated, thereby controlling the propagation phase. The combination of propagation phase and geometric phase enables independent degree-of-freedom control of polarization state and phase.

[0391] Metasurface engineering reverse design based on machine learning (ML) / deep learning (DL), such as large language modeling (LLM), involves starting from the desired modulation result and working backward to find the precise system, material, structure, or combination of factors that can produce that modulation result. ML / DL model-based metasurface engineering reverse design can generate configuration predictions for arbitrary morphology / topography superatoms / supercells (unit cells) within a predetermined range. Compared to standardized shapes such as cylindrical or cubic nanobody, free-form structural morphology design allows for the creation of metasurfaces with the desired modulation result within a finite time, significantly outperforming metasurface design based on traditional computer-simulated shapes. Free-form superatoms / unit cells achieve a high degree of manipulation freedom in the design space, simultaneously enabling beam exit angle deflection, phase, and polarization state modulation.

[0392] The future trend of machine learning in metasurface design lies in the deep integration of physical knowledge and artificial intelligence, as well as the construction of automated experimental closed-loop systems, thereby providing a core design engine for metasurface optical components.

[0393] In some instances, the eye illumination optics unit can be configured as a tunable wavelength polarization-state VCSEL illumination source, based on a MEMS microcavity consisting of a fixed dielectric Bragg mirror (DBR) and a MEMS-driven mirror. The cavity length is precisely controlled via piezoelectric actuation. Spectral tuning can achieve wavelength tuning at the Ångström level, with tuning resolution up to 1 Å (tunable to voltage step resolution), and an emission spectral wavelength bandwidth of 2-5 nm or narrower.

[0394] Simultaneously, polarization state control, as described above, utilizes spatially separated anisotropic structures (corresponding to x and y polarizations respectively) designed on a metasurface, and employs MEMS microcavities for selective enhancement, achieving high-speed voltage-controlled polarization switching with a switching time of less than 1 millisecond. It is compatible with CMOS processes and has a sub-0.1cc volume, making it suitable for deployment in head-mounted devices such as AI / AR glasses.

[0395] Furthermore, in all embodiments, the polarized eye illumination / imaging optics unit can utilize anisotropic or chiral nanocrystalline materials, such as perovskite nanomaterials, to achieve linearly polarized emission (LPL) and / or circularly polarized emission (CPL), along with corresponding polarization state detection. Another example is supramolecular helical nanowire circularly polarized emission (CPL), where chiral organic molecules form helical structures through hierarchical self-assembly, triggering a chiral optical response. Other methods include those based on quantum dot / rod nanocrystals, rare-earth-doped nanocrystals, and metallic nanocrystals.

[0396] In some embodiments, the polarized eye illumination optical unit can be configured to provide illumination based on polarization interference of a single-mode polarized VCSEL illumination source.

[0397] The eye illumination optical unit integrates a single-mode VCSEL illumination source with a subwavelength metasurface grating structure that locks polarized emission in a specific direction, as described above, and has a divergence angle of 25 degrees (1 / e). 2 The light is then uniformly emitted from the diffuser to illuminate the eye-tracking region (EYEBOX).

[0398] like Figure 11 The illumination imaging images shown are obtained from polarization interference and polarization scattering. The speckle pattern in the iris region is formed by the coherence of a single-mode polarized VCSEL, demonstrating the high reflectivity and multiple scattering characteristics of the iris's biological tissue. The sclera region shows less speckle, with microcirculatory vessels present, and exhibits predominantly polarization scattering.

[0399] Furthermore, as described above, the polarized eye illumination / imaging optical unit can also be configured for multispectral polarized illumination and polarized imaging in the visible-near-infrared (VIS-NIR) wavelength range. Some embodiments employ parallel and orthogonal polarization states for illumination / imaging, which can capture reflection or scattering information from ocular biological tissues at different wavelengths and depths. For example, short-wavelength green and blue light in the spectrum can be partially retained (linear polarization state) or chiral inverted (circular polarization state) after reflection from the surface or shallow layers (spectral reflection / diffuse reflection), while long-wavelength red and near-infrared light can penetrate deeper and form a depolarized state after backscattering through multiple scatterers.

[0400] Therefore, the combination of parallel polarization and orthogonal polarization in illumination / imaging configurations can capture complete polarization state information of biomarkers to generate characteristic high-contrast images for acquiring more comprehensive individual biological information.

[0401] While the examples in this article are provided for the eye, the configuration mechanisms discussed can be extended to other periocular biological tissues, such as subcutaneous biological tissues to which eyeglass nose pads adhere, multispectral / polarized / OAM modal illumination and imaging at visible-near-infrared (VIS-NIR) wavelengths, light propagation to the epidermis, dermis, and subcutaneous tissue, and the differences in absorption and scattering between melanosomes and blood vessels. To reduce volume, the illumination optics unit and the imaging illumination unit can be configured and integrated into a single unit.

[0402] In some embodiments, the illumination source (e.g., LED / VCSEL) and / or image sensor (photoelectric sensor, etc.) are monolithically integrated with metasurface optical elements using full-process CMOS semiconductor manufacturing, wafer-level optics (WLO), or planar optics processes. This integration enables nanometer-level pixel registration and optical axis alignment, ultimately packaged as a system-on-a-chip based on photonic integrated circuits.

[0403] Furthermore, all embodiments utilize dynamically tunable metasurface optical elements, enabling reconfigurable and programmable optical functions through nonlinear photonic devices, phase change materials (e.g., GST), liquid crystals, electro-optic effects, or mechanical strain.

[0404] Currently, a large body of evidence-based medicine has confirmed that photobiomodulation (PBM), through non-invasive low-level light therapy (LLLT), can stimulate cellular processes, regulate inflammatory pathways, enhance mitochondrial activity, and promote tissue regeneration, and has been established as one of the solutions for precision ophthalmology.

[0405] Photobiological biochemistry (PBM) is a nonthermal biological process that induces a series of physiological events by activating light of specific wavelengths through photoreceptor molecules. These light-induced biological changes activate a signaling cascade, driving cellular changes and ultimately improving cellular function and clinical outcomes. Cytochrome c oxidase (CcO), the IV complex of the mitochondrial respiratory chain, is the primary intracellular photoreceptor and transducer for red (600-750 nm) to near-infrared (750-1100 nm) (FR / NIR) light signals and is considered one of the main mechanisms of PBM effects. CcO is the terminal electron acceptor in the respiratory chain, catalyzing the electron transfer from cytochrome c to molecular oxygen, thereby promoting cellular bioenergy output due to increased oxidative phosphorylation, which promotes the synthesis of adenosine triphosphate (ATP). CcO contains two copper centers (CuA and CuB) and two erythrin centers (erythrin A and A3) that absorb infrared light. This photoreceptor interaction is hypothesized to alter the redox state of CcO, thereby increasing the electrochemical proton gradient and consequently increasing the production of mitochondrial membrane potential (MMP), ATP, and the second messenger cyclic adenosine monophosphate (cAMP).

[0406] Existing literature evidence suggests that FR / NIR light enhances the bioavailability of nitric oxide (NO) through multiple mechanisms. FR / NIR light enhances CcO activity by photodissociating NO from its CcO binding sites. FR / NIR light also promotes NO synthesis and photodissociates NO from hemoglobin and myoglobin. Redox changes, nitric oxide, and calcium ionization activate transcription factors, leading to increased gene expression.

[0407] PBM-induced transcriptional alterations lead to upregulation of antioxidant pathway genes, immune regulation, increased mitochondrial biogeneration, changes in mitochondrial fusion and fission, and improved cell viability. The effects of PBM on CcO and mitochondrial export have been documented in various experimental and clinical models and tissues, supporting the hypothesis that PBM is a major mechanism underlying the beneficial effects of PBM.

[0408] Therefore, mitochondria are crucial for regulating cellular health and disease progression. Mitochondrial dysfunction, oxidative damage, and inflammation are hallmarks of many degenerative diseases.

[0409] Photons are absorbed by mitochondria within cells (the primary receptor being cytochrome c oxidase CcO). Red and near-infrared radiation can dissociate nitric oxide in cytochrome c oxidase, thereby increasing the contact between oxygen and cytochrome c oxidase, which in turn promotes mitochondrial respiration, increases ATP synthesis, and alters intracellular oxidation levels. Furthermore, red radiation can regulate the release of cellular inflammatory factors, thereby inhibiting inflammation. Therefore, photonic biotherapy (PBM) may have bio-optical therapeutic effects on diseases related to energy abnormalities and inflammation.

[0410] PBM may be suitable for the treatment of: eye diseases such as age-related macular degeneration (AMD), retinitis pigmentosa (RP), diabetic retinopathy (DR) and diabetic macular edema (DME), dry eye disease (DED), especially meibomian gland dysfunction (MGD), ocular surface and eyelid diseases such as chalazion, stye, blepharitis and ocular rosacea, myopia, refractive amblyopia, strabismic amblyopia, retinal vascular dysplasia, primary open-angle glaucoma, etc.

[0411] The eye illumination optical unit can be configured with working modes, including but not limited to: photon biomodulation therapy working mode and eye biotissue illumination working mode.

[0412] In the photon biomodulation therapy mode, more combinations of LED light source positions / directions and higher LED light source radiation intensity or ocular irradiance / power density can be configured compared to the ocular biotissue illumination mode.

[0413] Correspondingly, the eye imaging optical unit can be configured with working modes, including but not limited to: photon biomodulation feedback monitoring working mode and eye biological tissue imaging working mode.

[0414] The photonic bio-regulation feedback monitoring mode can be configured with lower image sensor photoelectric conversion parameters compared to the ocular biological tissue imaging mode. These parameters are negatively correlated with the radiant intensity or ocular irradiance / power density of a predetermined LED illumination source.

[0415] In some instances, imaging parameters of the image sensor can be configured, such as digital / analog gain, photoelectric conversion gain, and synchronous integration time.

[0416] For acquiring images of ocular biological tissue, the control unit is configured to a first combined working mode. In response to the first combined working mode, the ocular illumination optical unit is configured to an ocular biological tissue illumination working mode and the ocular imaging optical unit is configured to an ocular biological tissue imaging working mode.

[0417] The embodiments of this invention utilize images of ocular biological tissues, including but not limited to images of the retina, choroid, cornea, sclera, and accessory ocular surface, to assess ocular health.

[0418] Accessory ocular surface health includes individual physiological attributes such as tear river height, non-contact tear film breakup time, lipid layer, blinking or blinking, conjunctiva and eyelid margin, and meibomian glands. Images of ocular biological tissues can be configured to predict ocular health status based on pre-trained machine learning (ML) / deep learning models through inference.

[0419] For photonic biomodulation therapy, the control unit is configured to a second combined working mode. In response to the second combined working mode, the eye illumination optical unit is configured to a photonic biomodulation therapy working mode and the eye imaging optical unit is configured to a photonic biomodulation feedback monitoring working mode.

[0420] The control unit monitors the eye closure status and photonic biomodulation therapy radiation dose (such as current ocular irradiance / power density) in real time through the photonic biomodulation feedback monitoring mode of the eye imaging optics unit. This feedback is used to activate or deactivate the photonic biomodulation therapy mode of the eye illumination optics unit. In some instances, if the eye is not closed or the ocular irradiance / power density exceeds radiation safety standards, the control unit deactivates the photonic biomodulation therapy mode. Conversely, if the eye is closed and the ocular irradiance / power density is within radiation safety standards, the control unit activates the photonic biomodulation therapy mode. In some instances, the power density of the ocular illumination optics unit under photonic biomodulation therapy mode is higher than that under ocular biological tissue acquisition mode.

[0421] In some embodiments, a photonic biomodulation therapy system includes:

[0422] Control unit, eye illumination optical unit, eye imaging optical unit;

[0423] The eye illumination optical unit is configured with the following working modes: photon biomodulation therapy working mode and eye biotissue illumination working mode;

[0424] The eye imaging optical unit is configured with the following working modes: photon biomodulation feedback monitoring working mode and eye biological tissue imaging working mode.

[0425] The control unit is configured in a first combined working mode for acquiring images of ocular biological tissues. In response to the first combined working mode, the ocular illumination optical unit is configured in an ocular biological tissue illumination working mode and the ocular imaging optical unit is configured in an ocular biological tissue imaging working mode.

[0426] The control unit is configured in a second combined operating mode for photonic biomodulation therapy. In response to the second combined operating mode, the eye illumination optical unit is configured in a photonic biomodulation therapy operating mode and the eye imaging optical unit is configured in a photonic biomodulation feedback monitoring operating mode.

[0427] In some embodiments, a photonic biomodulation therapy includes:

[0428] The control unit, the eye illumination optical unit, and the eye imaging optical unit;

[0429] The control unit is configured with a first combined operating mode. In response to the first combined operating mode, the eye illumination optical unit is configured to an eye biological tissue illumination operating mode and the eye imaging optical unit is configured to an eye biological tissue imaging operating mode to acquire eye biological tissue images; analyze the eye biological tissue images based on deep learning algorithms to assess the current eye health status; and / or acquire historical medical and health record data.

[0430] The control unit responds to the current eye health status and / or historical medical health record data to generate relevant treatment prescription parameters for photonic biomodulation;

[0431] The control unit responds to the treatment prescription parameters and configures a second combined working mode, wherein the eye illumination optical unit is configured as a photon biomodulation therapy working mode and the eye imaging optical unit is configured as a photon biomodulation feedback monitoring working mode.

[0432] The control unit activates the feedback monitoring working mode of the eye imaging optical unit and simultaneously activates the photon biomodulation therapy working mode of the eye illumination optical unit.

[0433] After completing the relevant prescription treatment for photonic biomodulation, the control unit deactivates the eye illumination optics unit and the eye imaging optics unit, and creates a treatment log, which is stored as historical medical and health record data.

[0434] Historical medical and health record data may be encrypted and stored on local non-volatile storage or uploaded to a specific encrypted data cloud for medical and health record data recording.

[0435] In some embodiments, the prescription parameters for photon biomodulation-related treatments can be configured with reinforcement learning-based personalized treatment path optimization, which autonomously optimizes the prescription parameters for each treatment to create an adaptive personalized treatment plan based on historical medical and health record data and efficacy feedback.

[0436] Prescription parameters for photon biomodulation-related therapies include, but are not limited to:

[0437] Data attributes include radiation wavelength, radiation dose (including power density and energy density, radiation exposure time), radiation pulse structure (frequency (Hz), duty cycle), and radiation optical properties.

[0438] PBM typically uses visible and near-infrared (NIR) wavelengths, each eliciting different biological responses. Red and near-infrared wavelengths are favored due to their deeper tissue penetration and efficient absorption by cytochrome C oxidase (CcO). Although shorter wavelengths such as blue and green light are less commonly used due to their higher photon energy, they show emerging anti-inflammatory and antibacterial potential. Various wavelengths, including blue, green, yellow, red, and near-infrared light, have been applied individually or in combination to ophthalmic diseases.

[0439] Photonic biomodulation can cover different depths of ocular biological tissues (periocular area, tarsal plate, cornea, iris, retina, etc.) to produce a synergistic effect.

[0440] Different wavelengths have different penetration depths and target chromophore affinities, such as:

[0441] 1. Yellow / green light (approximately 570-590 nm / 495-570 nm) penetrates biological tissues to a shallow depth. It has a high absorption band at wavelengths below 610 nm and acts on the superficial dermis.

[0442] The main targets and characteristics are: hemoglobin absorption peak: yellow light is located near the absorption peak of hemoglobin (especially oxyhemoglobin) and can be absorbed efficiently; vascular regulation and neural regulation; less melanin absorption.

[0443] 2. Red light (620-700 nm, commonly 630, 650, 670 nm) has a moderate penetration depth in biological tissues. In the visible light band of 610 to 700 nm, its penetration power increases by about 5 orders of magnitude, reaching the dermis and even subcutaneous tissue.

[0444] The main targets and characteristics are: Mitochondrial absorption: It can be effectively absorbed by CCO and is one of the core wavelengths that initiate the photon bioregulatory effect; fibroblast stimulation, strong anti-inflammatory and repair-promoting effects.

[0445] 3. Near-infrared light (700-1100 nm, commonly used 810 nm, 830 nm, 850 nm) Penetration depth: deepest.

[0446] The main targets and characteristics are: optimal tissue penetration, deep photonic biomodulation, neuroprotection and repair, and deep anti-inflammatory effects.

[0447] 4. Multi-wavelength combined light (590 nm + 630 / 650 / 670 nm + 810 / 830 / 850 nm) in red to near-infrared light waves is suitable for inducing PBM to treat dry eye syndrome (DED), especially meibomian gland dysfunction (MGD) and retinal diseases.

[0448] For example, stimulating CcO activity at a wavelength of 590 nm increases nitric oxide synthesis, promotes vasodilation, and improves local oxygenation in the target tissue. A wavelength of 650 nm promotes the binding of O2 to active CuB / Fea3 sites, while a wavelength of 850 nm drives electron transfer at the CuA sites of CcO. The results include upregulation of electron transport pathways, increased energy (ATP) production, reduced inflammation, enhanced cell viability, and reduced apoptosis.

[0449] From the perspective of photonic biomodulation, multi-wavelength combination working modes help optimize treatment parameters, induce positive effects at the cellular level, and ultimately promote the improvement of overall cellular state.

[0450] In some embodiments, the multi-wavelength combination operating mode can be configured such that different wavelengths perform sequential or superimposed accumulation with different radiation doses.

[0451] The dose-response relationship of photobiological biotherapy (PBM) depends on two parameters that determine dose and biological response: 1) irradiance (W / cm²) and 2) exposure time (seconds). The product of these two components is the radiation dose, expressed in J / cm². Irradiance and dose define the therapeutic photobiological modulatory response of a specific ocular tissue. Irradiance reflects the power density of light, which is crucial for understanding biological photoresponses, tissue penetration, and internal thermal effects, while energy density represents the transfer of radiation dose and is essential for establishing the dose-response relationship. Numerous studies have shown that, despite the same radiation dose (J / cm²), lower irradiance and longer exposure times are more therapeutically effective than relatively higher irradiance and shorter exposure times.

[0452] PBM exhibits a biphasic dose-response relationship, meaning that increasing irradiance or exposure time enhances the benefit up to an optimal threshold, beyond which photoinhibition may occur. The PBM dose-response curve corresponds to the Arndt–Schulz curve, where increasing the dose corresponds to an effect that increases to a maximum (dose window), after which further increases in dose will trigger a negative response. Optimal dosimetric parameters vary depending on the type of ocular tissue and wavelength, requiring the selection of the best treatment regimen.

[0453] In some instances, radiation can occur with the eye closed, and the energy density during this state can typically be several times higher than in the open state. In some cases, the energy density ranges from 0.1 to 50 J / cm², and the irradiance parameter ranges from 1 to 50 mW / cm². 2 between.

[0454] Radiation exposure time exhibits linear accumulation before the optimal threshold for PBM, with some instances showing exposure times ranging from 30 to 900 seconds.

[0455] In some embodiments, the multi-wavelength combination operating mode can be configured such that different wavelengths perform sequential or superimposed accumulation with different irradiance and exposure time.

[0456] Optimizing dosimetric parameters is crucial for minimizing adverse reactions while achieving therapeutic benefits.

[0457] In the operating mode of a pulsed radiation structure (e.g., frequency 1-10 Hz, duty cycle 10-50%), a pulsed radiation power density pulse may have a resonant frequency effect on the cell body, potentially providing better tissue penetration and therapeutic effects than in continuous operation mode. The mechanism of the pulsed radiation structure ensures that the temperature of the biological tissue remains below a safe coagulation threshold.

[0458] Prescription parameters for photonic biomodulation-related therapies also include radiation optical properties, including but not limited to: coherent state, light polarization state {0°, 90°, 45°, 135°, RCP, LCP} or combinations thereof, and orbital angular momentum (OAM) mode.

[0459] The advantages of coherent photons with different spectral wavelength bandwidths (such as 40nm, 20nm, 10nm, 3nm or smaller) may be that they have a photon superposition and combination effect on biological tissues and have therapeutic effects on different biological tissues of the eye under the same radiation dose conditions.

[0460] The advantages of polarized photons may include their direction-selective absorption effect on biological tissues. Different polarization states or their combinations of working modes of PBM can have therapeutic effects on different biological tissues of the eye under the same radiation dose. For example, the retinal nerve fiber layer (RNFL), the highly regular and layered collagen fibers in the corneal stroma, the Henle fiber layer in the macula, and lens fiber cells have polarization direction selectivity. Different orbital angular momentum (OAM) modes may have different biological tissue penetration and therapeutic effects.

[0461] In some embodiments, to enhance the therapeutic effect of photonic biomodulation, vitamin A supplementation and specific prescription doses of B vitamins with synergistic effects, such as vitamin B1 (thiamine), B3 (nicotinamide / niacin), and B12 (cobalamin), especially B3, are used. The core mechanism of B3 lies in energy metabolism support, enhancing mitochondrial function: promoting ATP synthesis to provide sufficient energy for nerve cells; activating protective pathways: NAD+ is an essential cofactor for sirtuins, regulating cellular stress responses, repairing DNA damage, and inhibiting inflammation, thereby enhancing cellular viability; and reducing oxidative stress: for example, large amounts of harmful free radicals are generated during glaucoma and optic nerve diseases. Sufficient NAD+ helps maintain the cell's antioxidant defense system and reduce oxidative damage. Other optional prescriptions include, but are not limited to: supplementation with Omega-3 fatty acids and / or antioxidants including vitamin C, vitamin E, zinc, selenium, and plant compounds such as lutein and zeaxanthin.

[0462] The control unit can be implemented as a processor and memory. In some examples, the control unit can be implemented as hardware, software, and / or a combination of hardware and software in an HMD. In some examples, the control unit can be implemented wholly or partially by any type of application, program, library, script, task, service, process, or executable instructions of any form or type that execute on any type of hardware, such as circuitry that may include digital and / or analog elements, like transistors, logic gates, registers, memory devices, resistive elements, conductive elements, capacitive elements, and / or the like, as understood by one of ordinary skill in the art. In some examples, the processor can be implemented as a general-purpose single-chip and / or multi-chip processor, a single-core and / or multi-core processor, a digital signal processor (DSP), an application-specific integrated circuit (ASIC), a field-programmable gate array (FPGA) or other programmable logic device, discrete gate or transistor logic, discrete hardware components, and / or any combination for performing the functions described herein. A general-purpose processor can be any conventional processor, microprocessor, controller, microcontroller, and / or state machine. In some examples, memory may be implemented by one or more components (e.g., random access memory (RAM), read-only memory (ROM), flash or solid-state memory, hard disk storage, etc.) for storing data and / or computer-executable instructions to perform and / or facilitate the processing and storage functions described herein. In such examples, memory may be volatile and / or non-volatile memory and may include database components, object code components, scripting components, or any other type of information structure suitable for implementing the various activities and storage functions described herein.

[0463] Furthermore, the parameters, structures, methods, etc., mentioned in this invention should not be narrowly interpreted as limiting the configuration of specific embodiments. Although various inventive embodiments have been described and illustrated herein, those skilled in the art will readily conceive of a variety of other means and / or structures for performing the described functions and / or obtaining the described results and / or one or more advantages described herein, and each such variation and / or modification is considered to be within the scope of the inventive embodiments described herein. More generally, those skilled in the art will readily understand that all parameters, dimensions, materials, and configurations described herein are exemplary, and actual parameters, dimensions, materials, and / or configurations will depend on the specific application or application to which the inventive teachings are used. Those skilled in the art will recognize or be able to determine many equivalents of the specific inventive embodiments described herein using no more than conventional experimentation. Therefore, it should be understood that the foregoing embodiments are presented by way of example only, and that inventive embodiments may be practiced in ways other than the specific description and claims within the scope of the appended claims and their equivalents. Furthermore, it should be understood that all definitions defined and used herein shall govern and take precedence over dictionary definitions, definitions in documents incorporated by reference, and / or the general meaning of the defined terms. Therefore, the claims are not limited to the specific terms used in the description itself and may be implemented in various variations. Furthermore, the contents of this application, including the specification and drawings—including but not limited to parametric data, geometric scales, orientation / symbol conventions, structural stacking relationships, relative physical spatial relationships, physical-logical coupling relationships, and content-based narrow inferences or derivations—should not be used as the basis for exclusive or restrictive definitions, but should be considered as limited examples. Construction extensions, variations, or equivalent implementations based on the general principles of this invention should be considered to fall within the protection scope of this application.

Claims

1. A photon biomodulation therapy system for a head-mounted device, comprising: Control unit, eye illumination optical unit, eye imaging optical unit; The eye illumination optical unit is configured with the following working modes: photon biomodulation therapy working mode and eye biotissue illumination working mode; The eye imaging optical unit is configured with the following working modes: photon biomodulation feedback monitoring working mode and eye biological tissue imaging working mode. The control unit is configured in a first combined working mode for acquiring images of ocular biological tissues. In response to the first combined working mode, the ocular illumination optical unit is configured in an ocular biological tissue illumination working mode and the ocular imaging optical unit is configured in an ocular biological tissue imaging working mode. The control unit is configured in a second combined operating mode for photonic biomodulation therapy. In response to the second combined operating mode, the eye illumination optical unit is configured in a photonic biomodulation therapy operating mode and the eye imaging optical unit is configured in a photonic biomodulation feedback monitoring operating mode.

2. The photon biomodulation therapy system for a head-mounted device according to claim 1, characterized in that, The control unit detects the eye closure state and photonic biomodulation therapy radiation dose in real time through the photonic biomodulation feedback monitoring working mode of the eye imaging optical unit. This is used to provide feedback to activate or deactivate the photonic biomodulation therapy working mode of the eye illumination optical unit. The power density in the photonic biomodulation therapy working mode of the eye illumination optical unit is greater than the power density in the eye biological tissue acquisition working mode.

3. The photon biomodulation therapy system for a head-mounted device according to claim 1, characterized in that, The eye illumination optical unit and / or eye imaging optical unit may be configured with metasurface-based optical elements, which may be configured to perform coherent state, orbital angular momentum (OAM) mode, wavelength dimension, and polarization dimension optical modulation functions on incident light in any combination.

4. A photonic biomodulation therapy method for a head-mounted device, comprising: Control unit, eye illumination optical unit, eye imaging optical unit; The control unit is configured with a first combined operating mode, and responds to the first combined operating mode. The eye illumination optical unit is configured in an eye biological tissue illumination working mode and the eye imaging optical unit is configured in an eye biological tissue imaging working mode to acquire eye biological tissue images; Assess current eye health status by analyzing images of ocular biological tissues using deep learning algorithms; and / or obtain historical medical and health record data; The control unit responds to the current eye health status and / or historical medical health record data to generate relevant treatment prescription parameters for photonic biomodulation; The control unit responds to the treatment prescription parameters and configures a second combined working mode, wherein the eye illumination optical unit is configured as a photon biomodulation therapy working mode and the eye imaging optical unit is configured as a photon biomodulation feedback monitoring working mode. The control unit activates the feedback monitoring working mode of the eye imaging optical unit and simultaneously activates the photon biomodulation therapy working mode of the eye illumination optical unit. After completing the relevant prescription treatment for photonic biomodulation, the control unit deactivates the eye illumination optics unit and the eye imaging optics unit, and creates a treatment log, which is stored as historical medical and health record data.

5. The photon biomodulation therapy method for a head-mounted device according to claim 4, characterized in that, The historical medical and health record data is encrypted and stored in local non-volatile memory or uploaded to a specific encrypted data cloud for medical and health record data recording.

6. The photon biomodulation therapy method for a head-mounted device according to claim 4, characterized in that, The prescribed parameters for photon biomodulation-related treatments include at least: radiation wavelength, radiation dose, radiation pulse structure, and radiation optical property data.

7. The photon biomodulation therapy method for a head-mounted device according to claim 6, characterized in that, The radiation wavelengths are configured to include: yellow light 570-590 nm; green light 495-570 nm; red light 620-700 nm; near-infrared light 700-1100 nm, or any combination of the above wavelengths.

8. The photon biomodulation therapy method for a head-mounted device according to claim 6, characterized in that, The radiation dose includes: energy density, irradiance parameter, and radiation exposure time; the energy density parameter is configured to range from 0.1 to 50 J / cm², and the irradiance parameter is configured to range from 1 to 50 mW / cm². 2 The radiation exposure time range is configured to be between 30 and 900 seconds.

9. The photonic biomodulation therapy method for a head-mounted device according to claim 6, characterized in that, The radiation pulse structure is configured to operate in a frequency range of 1-10 Hz and a duty cycle of 10-50%.

10. The photonic biomodulation therapy method for a head-mounted device according to claim 6, characterized in that, The radiation optical properties are configured as: coherent state, optical polarization state 0°, 90°, 45°, 135°, RCP, LCP or a combination thereof, and any one of the orbital angular momentum (OAM) modes.

11. The photonic biomodulation therapy method for a head-mounted device according to claim 7 or 8, characterized in that, The prescription parameters for photon biomodulation-related therapy are configured in a multi-wavelength combination working mode, wherein different wavelengths are configured to perform sequential or superimposed accumulation with different irradiance and radiation exposure time.

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