Liquid lens, contact lens comprising liquid lens, and intraocular device

Abstract

The present set relates to optical elements having variable characteristics, and in particular to liquid lenses having variable power, and functional enhanced contact lenses equipped with such liquid lenses. The liquid lens is implemented as a capsule comprising a control electrode, an immiscible first liquid medium having a refractive index n1 and a second liquid medium having a refractive index n2, such that n2gt; n1. One of the liquid media is adapted to be controlled by an electromagnetic field by means of the electrode. The second liquid medium represents a colloidal system formed from a liquid and solid high refractive index nanoparticles, the refractive index of the nanoparticles being higher than the refractive index of the liquid. According to the liquid lens, the achievable focal power range is expanded, so that the potential application field of the liquid lens can be expanded. In a first embodiment, a contact lens equipped with the aforementioned liquid lens can implement a zoom function, in a second embodiment, when used with a microdisplay, an AR / VR / XR mode can be implemented, and in a third embodiment, when used with a light emitting diode, a myopia prevention and treatment function can be implemented. Intraocular devices equipped with the above liquid lens can replace the user's lens and also have enhanced functionality.

Description

Technical Field

[0001] This invention relates to optical elements with variable properties, particularly to liquid lenses with variable optical power, and contact lenses comprising the liquid lens, wherein the contact lenses can be used to generate magnified images of objects within a field of view to form augmented reality, virtual reality, or extended reality (AR / VR / XR) for the prevention and treatment of myopia, and also to intraocular lenses. Background Technology

[0002] As is well known, the human eye has a vertical field of view of approximately 120° and a horizontal field of view of approximately 180° (this is also true for monochromatic vision, even when both eyes are observing simultaneously). Furthermore, when the lens focuses on objects at different distances (accommodation), it changes the curvature of the posterior wall of the eye (vitreous humor) and the corresponding focal length, thus altering the focusing distance. In healthy individuals, the lens can change its curvature, allowing for a range of optical power variation of approximately 19 to 33 diopters. However, without any additional external equipment, the human eye's optical system cannot autonomously expand its field of view (the ratio between the linear or angular dimensions of the image and the object).

[0003] Optical magnification, or variable-angle magnification, i.e., zoom functionality, in optical systems can be achieved using devices such as zoom lenses, variable-length lenses, or varifocal lenses. Optical magnification in these traditional systems is achieved by changing the focal length by moving individual lens elements within the lens holder—the smaller the focal length of the optical system, the larger the field of view, and vice versa. The changes in focal length and the corresponding field of view can be gradual or smooth (adjustable at will). However, such lenses can contain more than 10-20 lens elements, meaning they cannot have a compact design, making it impossible to incorporate them into wearable devices without causing significant user discomfort.

[0004] Prior art discloses a liquid lens implemented as a capsule containing an immiscible first liquid medium having a refractive index n1 and a second liquid medium having a refractive index n2, such that n2 > n1, and control electrodes, wherein one of the liquid media is adapted to be controlled by an electromagnetic field via the electrodes (see publication WO2020132443A2, classification G02B 26 / 00, published June 25, 2020). In prior art devices, the first liquid is an aqueous solution of one or more electrolytes, while the second liquid represents silicone oil or an alkane, which allows for a maximum refractive index difference Δn = n2 - n1 of approximately 0.05. The optical power of this lens can vary according to the curvature of the free meniscus of the liquid, which is controlled by an electromagnetic field, ranging from 0 (for a flat meniscus) to approximately 10 diopters. It is proposed to integrate this liquid lens as a reconfigurable optical system with a power supply and control module into a contact lens, which would allow the resulting device to be used for vision correction. The main drawback of existing technical solutions is that their functionality is very limited: the difference in refractive index of simple (ordinary, common) liquids is very small (not exceeding 0.1), which only allows the optical power of the liquid lens to change within a relatively small range. This limits its application, and it can only be used as a component to compensate for the defects of natural adjustment, rather than for zoom functions.

[0005] Another current challenge is creating compact AR, VR, and XR devices based on LED microdisplays.

[0006] Prior art discloses a contact lens for creating augmented or extended reality, comprising a display with its screen facing the user's eyes, a power supply and control module, and a sleeve-type collimating optical system disposed between the display and the eye (see patent US10353205B2, classification G02C 7 / 04, published July 16, 2019). The collimating optical system operates based on multiple reflections of light: an image from a light source (display) in the form of diverging rays travels along the device chamber and is reflected by a "secondary" convex mirror, returning and being reflected by a "primary" concave mirror whose focal point is located on the "secondary" mirror. Therefore, the image reflected from the "secondary" mirror exits as a collimated beam from the chamber aperture, reaches the user's eye, and the user's eye, in turn, focuses the image onto the retina.

[0007] This femtoprojector optical system can form a magnified display image on the user's retina, and its system size allows the display device to be integrated into contact lenses. However, a major drawback of existing devices is their relatively large thickness (approximately 2mm), making them quite uncomfortable to use. Furthermore, existing devices are difficult to manufacture and adjust in terms of optical components, have a limited field of view, and form an uneven light pattern on the retina. Such projectors always have "parasitic" peripheral rays from the light source that are not projected onto the "secondary" mirror and exit from the chamber aperture as diverging beams. These rays do not focus on the retina but instead appear as diverging rays, resulting in optical aberrations and blurry spots in the background of the focused display image, while also reducing the brightness of the resulting image on the retina because some of the light has been scattered.

[0008] Vision correction applications represent another trend in the functional expansion of wearable optical devices in the form of contact lenses. The human eye possesses a natural ability to adjust, focusing its gaze on objects in the external world located at different distances from the observer. The contraction and relaxation of the ciliary muscle provides a change in the radius of the posterior wall of the lens, focusing the image onto the retina.

[0009] One of the most common vision problems is nearsightedness (myopia). Due to this visual abnormality, a person has a good ability to distinguish near objects, but the eye cannot focus clearly on distant objects (including objects at infinity), thus making distant objects appear blurry. Myopia, as a refractive (deflection) abnormality, may occur because the eye itself is elongated, so even when the lens is fully relaxed, the image of a distant object focuses at a distance in front of the retina, rather than on the retina. Furthermore, myopia can occur due to prolonged screen time on computers or continuous use of electronic devices (when the lens is under stress for most of the day), and it may also be a result of a genetic predisposition.

[0010] One known method for slowing down, preventing the development of, and even partially curing myopia is called myopia defocusing, which involves creating a "stimulus" such as a defocused image around the retina. This stimulation inhibits the longitudinal growth of the eye and slows down or stops the development of myopia. Prior art discloses a device for preventing and treating myopia (shortsightedness), implemented as a contact lens, including four light-emitting diodes (LEDs) disposed on the peripheral portion of the contact lens and facing the user's eye, a power supply and control module, and an optical system disposed between the LEDs and the eye (see publication WO2021056018A1, classification G02C11 / 04, published March 25, 2021). In this prior art device, the optical system is based on refractive elements (micromirrors) that focus the emission from the LEDs near the user's retina, so that the user unconsciously intends to generate an image of the focused point (spot), thereby training the eye muscles and enabling the prevention and treatment of myopia in its early stages. The disadvantages of this prior art device are that it requires consideration of the individual characteristics of the user's vision, the adjustment of the refractive elements is complex, and the degree of defocus of the LED image cannot be adjusted during treatment.

[0011] Another common vision impairment (affecting more than 8% of people over 50) is cataracts, which are partial or complete clouding of the lens, leading to significant vision loss and reversible blindness. To treat blindness caused by lens damage (e.g., due to cataracts, glaucoma, physical injury, etc.), surgical intervention is recommended to remove the damaged lens and replace it, for example, with an intraocular lens. Once the natural lens is removed, a regular monofocal or multifocal intraocular lens can be implanted in the posterior chamber of the eye. The problem with this device is the lack of natural accommodation. Therefore, to focus on near objects, users of intraocular lenses must use additional optical devices, such as glasses or contact lenses.

[0012] Prior art discloses an intraocular device comprising an intraocular lens adapted to be adjusted according to a user's control signals, and a retaining element that holds the intraocular lens within the user's eye (see patent US8377125B2, classification A61F2 / 16, published February 19, 2013). In prior art devices, the retaining element, which provides adjustment for a specific flexible protuberance (called a tactile element), utilizes the tension of the ciliary muscle to alter the position of the intraocular lens along the optical axis of the eye, as well as the optical power of the intraocular lens. A disadvantage of this method is the need for periodic intraocular injections of ciliary muscle relaxants during the postoperative period—the healing period (2 to 3 weeks)—to keep the ciliary muscle relaxed until fibrosis is complete. Drug relaxation of the ciliary muscle prevents its contraction and fixes the lens capsule. Another disadvantage is that physical movement along the optical axis depends on the tension of the ciliary muscle, which can be imperfect and may provide incomplete accommodation.

[0013] Therefore, the technical problem is to eliminate the aforementioned shortcomings of existing technologies and create compact wearable optical devices in the form of contact lenses and intraocular devices with extended functions. Summary of the Invention

[0014] Regarding the liquid lens design, the technical advantage lies in significantly expanding its potential application areas by extending the achievable optical power range. The technical solution in the liquid lens addresses the established problems and achieves the desired effect. The liquid lens is implemented as a capsule containing an immiscible first liquid medium with a refractive index n1 and a second liquid medium with a refractive index n2 such that n2 > n1, as well as control electrodes. One of the liquid media is suitable for control via an electromagnetic field using the electrodes, and the second liquid medium represents a colloidal system formed from liquid and solid high-refractive-index nanoparticles, where the refractive index of the nanoparticles is higher than that of the liquid. The first and second liquid media are preferably implemented with their refractive index difference Δn = n2 - n1 > 1.5. High refractive index nanoparticles can be made from ZnO, TiO2, ZnS, MgO, BeO, PbF2, CsI, HfO2, Sc2O3, SiN, GaP, CsPbBr3, CsPbCl3, CsPbI3, GaN, YVO4, MgAlO, YAlO, LuAlO, AlSb, GaSb, InSb, AlAs, GaAs, InAs, BC, SiC, TiC, VC, CsCl, CuCl, BaF, CeF3, LaF3, LiF , SrF2, LiI, KI, RbI, CaMoO4, SrMoO4, PbMoO4, LiNbO3, KNbO3, VN, ZrO2, GeO2, TeO2, WO3, Fe2O3, Y2O3, Lu2O3, Nb2O5, Ta2O5, Fe3O4, InP, CdSe, PbSe, ZnSe, AgGaS2, CdGa2S4, CdS, CuGaS2, CdTe, Te, ZnTe, BaTiO3, Bi4Ti3O 12PbTiO3, SrTiO3, diamond, or van der Waals materials composed of two-dimensional layers bonded together by van der Waals forces, such as graphite, graphene, graphene oxide, MoS2, WS2, MoSe2, WSe2, Cd3As2, Cd3Sb2, Cr2AlC, Cr2C, Mn2AlC, Mo2C, Mo2Ga2C, Mo3AlC2, Nb2AlC, Nb2C, Nb4AlC3, Nb4C3, Ta2C, Ta4AlC3 , Ti2AlC, Ti2AlN, Ti2C, Ti2N, Ti3AlC2, Ti3C2, Ti3CN, Ti3SiC2, Ti4N3, V2AlC, V2C, V4AlC3, V4C3, SnS2, SnSe2, ReS2, ReSe2, hBN, GaSe, Sb2Te3, PdS2, PdSe2, PtS2, PtSe2, GaS, GaTe, Ca(OH)2, K(FeMg)3Si3AlO 10 (OH)2, Mg(OH)2, MnO2, MoO3, Sb2O3, Sb2OS2, Sb2Se3, Sb2S3, As2S3, As2Te3, Bi2O2Se, Bi2Se3, Bi2TeO2, BiSbTe3, Bi2S 3. Bi2Te3, AsP, CdI2, CdPS3, CuS, CoPS3, Cr2Ge2Te6, Cr2S3, CrBr3, CrCl3, CrGeTe3, CrPS4, CrSeBr, CuCrP2S6, CuIn7Se 11 , FeCl2, FePS3, FePSe3, MoTe2, GaGeTe, GaInS3, GaSeTe, GaSSe, GaPS4, GaSTe, GeAs, GeSe, GeS, GeS2, GeTe, HfSe2, HfS2, HfTe2, In2S3, In2Se3, InSe, InTe, InGaSe2, InSeBr, InSnSe, MnPS3, MnPSe3, MoSSe, MoWSe2, MoWS2, MoWTe2, MoNbSe2, MoO 2.5 Cl 0.5, MoReS2, MoTaSe2, MoVSe2, Na2Co2TeO6, Nb2SiTe4, NbReS2, NbReSe2, NbS3, Ni2SiTe4, Ni3TeO6, NiCl2, NiI2, NiPS3, PbI2, PbTe, PtTe2, ReMoS2, ReNbS2, ReNbSe2, ReSSe, SbAsS3, SbSe, SbSI, SiP, SnPSe3, SnS, Ta2NiS5, TaS2, TaS3, TaSe2, TaWSe2, TlSe, TiBr3, SnTe2, TiS3, TlGaS2, TlGaSe2, TlGaTe2, TlInS2, WTe2, WSSe, WNbSe2, WReSe2, ZrS2, ZnIn2S4, ZnPS3, ZnPSe3, ZrGeTe4, ZrS3, ZrSe2, ZrSe3, ZrTe2, ZrTe3, Cr2Si2Te6, Cr2Te3, CrI3, CrSBr, CrTe2, Fe3GeTe2, Fe4GeTe2, TaCo2Te2, VS2, VSe2, VTe2, BiSbTeSe, BiTe, CuFeTe, HfTe5, FeSe, FeTeSe, FeTe, NbS2, NbSe2, NbTe2, NbTe4, NiTe2, PdBi2, PdTe2, SnTaS2, TaTe2, TiTe2, Tl2Ba2CaCu2O8, ZrSiS, CdAs2, CuSi2P3, NbAs2, PbTaSe2, Ta2NiSe5, Ta2NiTe5, Ta2Se8I, TaNi2Te3, TiS2, TiSe2, WNbTe2, ZnAs2, ZrTe5, LaTe2, NbSe3, Bi2SeTe2, Bi2Te2S, BiInTe3, Bi2Se 1.5 Te 1.5 , Bi4Te 1.5 S 1.5 , GeBi2Te4, PbBi2Te4, SnBi4Te7, SnSb2Te4, NiTe, SbTe, SiTe2, BiTeI, InSSe, PbSnS2, TlGaS3, C3N4, Cu2Te, GeSeTe, MnTe, As2Se3, CrPS3, SnSe, WReS2, TiBr, BaTiS3, Al2O3, BiFeO3, Ag3AsS3, HgS, bismuth strontium calcium copper oxide, black arsenic or black phosphorus.

[0015] Regarding the contact lens design according to the first embodiment, the technical effect lies in expanding its functionality by achieving a magnification function (zoom function) of the image of objects within the field of vision. In this regard, the setting problem is solved and the technical effect is achieved by the following method: the contact lens includes a power supply and control module and a reconfigurable optical system equipped with the aforementioned suggested liquid lens, which occupies at least a portion of the user's field of vision and is adapted to focus the image of objects located within this portion of the field of vision onto the user's lens, providing visible magnification of these objects. In this case, the optical power of the liquid lens preferably includes not less than 300 diopters and is capable of magnifying objects within the field of vision by at least two times. The portion of the field of vision occupied by the liquid lens may include 30% to 60%.

[0016] Regarding the contact lens design according to the second embodiment, the technical effect is to reduce the overall size of the contact lens with augmented reality, virtual reality, or extended reality (AR, VR, XR) functionality. In this regard, the setting problem is solved and the technical effect is achieved by the following method: the contact lens includes a display with the screen facing the user's eyes, a power supply and control module, and an optical system equipped with the aforementioned suggested liquid lens, which is adapted to focus the emission from the screen onto the user's lens. In this case, the optical power of the liquid lens preferably includes not less than 800 diopters. The liquid lens can be mounted with a gap relative to the screen, wherein the gap is formed by a hollow cavity or a layer of polymer material.

[0017] Regarding the contact lens design according to the third embodiment, the technical effect lies in expanding the range of possible therapeutic interventions by providing the possibility of altering the degree of defocus of the image formed on the user's retina. In this regard, the setting problem is solved and the technical effect is achieved by the following method: the contact lens includes at least one light-emitting diode (LED) disposed on the peripheral portion of the contact lens and facing the user's eye, a power supply and control module, and an optical system equipped with the aforementioned suggested liquid lens, which is adapted to focus the emission from the LED in front of the user's retina. In this case, the optical power of the liquid lens includes not less than 1000 diopters. The liquid lens is preferably adapted to alter the degree of defocus of the LED emission on the user's retina within the range of 0.5 to 10 diopters. In this case, the contact lens may have 2 to 40 LEDs disposed on its peripheral portion.

[0018] Regarding intraocular devices, the technical advantage lies in expanding their functionality, particularly by enhancing accommodative capabilities to a level exceeding the physiological capabilities of the human eye. In this regard, the setup problem is solved and the technical advantage achieved by the following approach: the intraocular device comprises an intraocular lens adapted for adjustment according to a user's control signal and a holding element that secures the intraocular lens within the user's eye. The intraocular lens is equipped with the aforementioned suggested liquid lens, as well as a power supply and control module configured to convert the user's control signal into an electromagnetic field formed by the control electrodes of the liquid lens. The power supply and control module is preferably configured to change the optical power of the liquid lens from at least 19 diopters to 33 diopters, or up to a maximum of 200 diopters. In this case, the power supply and control module is preferably configured to send an activation signal to a light-emitting diode in the contact lens when the optical power of the liquid lens exceeds 35 diopters. The liquid lens capsule is preferably made of an elastic polymer material, while the holding element may be integrally formed with the liquid lens capsule. The holding element may be implemented as a lug formed of an elastic polymer material. Attached Figure Description

[0019] Figure 1

[0020] Figure 1 This is a cross-sectional view of the disclosed liquid lens with an inactive electromagnetic field;

[0021] Figure 2

[0022] Figure 2 and Figure 1 Similarly, it has an electromagnetic field that is activated to its maximum.

[0023] Figure 3

[0024] Figure 3 It is a contact lens according to the first embodiment, which has 100% field of vision coverage and an inactive zoom function;

[0025] Figure 4

[0026] Figure 4 and Figure 3 Similarly, it has an activated zoom function;

[0027] Figure 5

[0028] Figure 5 It is a schematic diagram of an image formed by a contact lens with 100% field of view coverage and inactive zoom function according to the first embodiment;

[0029] Figure 6

[0030] Figure 6and Figure 5 Similarly, it has an activated zoom function;

[0031] Figure 7

[0032] Figure 7 It is a contact lens according to the first embodiment, which has 50% field of vision coverage and inactive zoom function;

[0033] Figure 8

[0034] Figure 8 and Figure 7 Similarly, it has an activated zoom function;

[0035] Figure 9

[0036] Figure 9 It is a schematic diagram of a contact lens with 50% field of view coverage and activated zoom function forming a magnified image according to the first embodiment;

[0037] Figure 10

[0038] Figure 10 The implementation is shown according to Figure 9 The solution is an image that is visible to the eye;

[0039] Figure 11

[0040] Figure 11 A projection system based on a liquid lens is shown, wherein the liquid lens is arranged relative to a display and has an air gap formed by a hollow chamber;

[0041] Figure 12

[0042] Figure 12 A liquid lens-based projection system is shown, wherein the liquid lens is arranged relative to a display and has gaps formed by layers of polymer material.

[0043] Figure 13

[0044] Figure 13 It is a cross-sectional view of an image formed using a contact lens with AR / VR / XR functionality according to the second embodiment;

[0045] Figure 14

[0046] Figure 14 A front view of a contact lens with AR / VR / XR functionality according to a second embodiment is shown;

[0047] Figure 15

[0048] Figure 15 It is a schematic diagram of forming an image using a contact lens with myopia correction function according to a third embodiment, which is equipped with a light-emitting diode;

[0049] Figure 16

[0050] Figure 16 This is a schematic diagram of forming an image using a contact lens according to a third embodiment, which is equipped with multiple light-emitting diodes;

[0051] Figure 17

[0052] Figure 17 A front view of a contact lens with 16 light-emitting diodes according to a third embodiment is shown;

[0053] Figures 18-20

[0054] Figures 18-20 An overall view of the disclosed intraocular device with various retaining elements is shown;

[0055] Figure 21

[0056] Figure 21 The installation of the intraocular device in front of the iris of the user's eye is shown;

[0057] Figure 22

[0058] Figure 22 This is a schematic diagram of an image formed using the disclosed intraocular device mounted behind the iris when the lens is adjusted to infinity (19 diopters of liquid lens power);

[0059] Figure 23

[0060] Figure 23 and Figure 22 The procedure is the same, but is performed when the lens is adjusted to near the physiological point (33 diopters of liquid lens power).

[0061] Figure 24

[0062] Figure 24 and Figures 22-23 The same, but when achieving macro vision mode (liquid lens with an optical power of 138 diopters and a thickness of 1 mm). Detailed Implementation

[0063] The proposed invention relates to a design using a liquid lens 1, which includes a capsule 2 and a control electrode 3 disposed on the outer periphery. Figures 1-2The inlet and outlet windows of capsule 2 are made of a material transparent in the visible spectrum, such as glass, crystal, nanoglass ceramics, or optically transparent polymers. Capsule 2 contains two immiscible (non-wetting, with different viscosities) liquid media with different refractive indices, one of which (either) is suitable for control via an electromagnetic field using electrode 3. This allows control over the curvature of the interface (i.e., meniscus 4) between the liquid media. To achieve this control, one of the media may contain magnetic nanoparticles and / or have high electrical conductivity.

[0064] The first liquid medium 5 is, for example, water or an aqueous solution, having a refractive index n1 in the visible range, wherein n1 includes 1.2 to 1.4. A refractive index lower than that of water (1.33) can be achieved by introducing porous nanoparticles made of materials with low refractive indices and low extinction coefficients in the visible spectrum (e.g., SiO2, TiN, HfN, ZrN, YN, VN, WN). These nanoparticles can be synthesized in deionized water using femtosecond laser ablation under conditions that induce the catalytic decomposition of water into hydrogen and oxygen. The lower the n1, the higher the maximum optical power achievable using the liquid lens 1.

[0065] The second liquid medium 6 represents a colloidal system having a refractive index n2, such that n2 > n1. This colloidal system is formed from a high-refractive-index impregnating liquid, for example, a hydrophobic oil with a refractive index of 1.4 to 1.8, and solid high-refractive-index nanoparticles 7 with a size of 2 to 250 nm and a low extinction coefficient. The refractive index of the nanoparticles 7 in the visible range is higher than that of the impregnating liquid, and includes 1.8 to 3, preferably 3. By achieving a refractive index difference Δn = n2 - n1 > 1.5, the optical power of the obtained liquid lens 1 can be significantly extended.

[0066] The high refractive index material used for nanoparticles 7 can be represented by non-layered materials with high refractive index and high transparency in the visible range, such as ZnO, TiO2, ZnS, MgO, BeO, PbF2, CsI, HfO2, Sc2O3, SiN, GaP, CsPbBr3, CsPbCl3, CsPbI3, GaN, YVO4, MgAlO, YAlO, LuAlO, AlSb, GaSb, InSb, AlAs, GaAs, InAs, BC, SiC, TiC, VC, CsCl, CuCl , BaF, CeF3, LaF3, LiF, SrF2, LiI, KI, RbI, CaMoO4, SrMoO4, PbMoO4, LiNbO3, KNbO3, VN, ZrO2, GeO2, TeO2, WO3, Fe2O3, Y2 O3, Lu2O3, Nb2O5, Ta2O5, Fe3O4, InP, CdSe, PbSe, ZnSe, AgGaS2, CdGa2S4, CdS, CuGaS2, CdTe, Te, ZnTe, BaTiO3, Bi4Ti3O 12 PbTiO3, SrTiO3, or diamond. However, the most promising materials appear to be van der Waals materials composed of two-dimensional layers bonded together by van der Waals forces: graphite, graphene, graphene oxide, MoS2, WS2, MoSe2, WSe2, Cd3As2, Cd3Sb2, Cr2AlC, Cr2C, Mn2AlC, Mo2C, Mo2Ga2C, Mo3AlC2, Nb2AlC, Nb2C, Nb4AlC3, Nb4C3, Ta2C, Ta4AlC3, Ti2Al lC, Ti2AlN, Ti2C, Ti2N, Ti3AlC2, Ti3C2, Ti3CN, Ti3SiC2, Ti4N3, V2AlC, V2C, V4AlC3, V4C3, SnS2, Sn Se2, ReS2, ReSe2, hBN, GaSe, Sb2Te3, PdS2, PdSe2, PtS2, PtSe2, GaS, GaTe, Ca(OH)2, K(FeMg)3Si3AlO 10 (OH)2, Mg(OH)2, MnO2, MoO3, Sb2O3, Sb2OS2, Sb2Se3, Sb2S3, As2S3, As2Te3, Bi2O2Se, Bi2Se3, Bi2TeO2, BiSbTe3, Bi2S 3. Bi2Te3, AsP, CdI2, CdPS3, CuS, CoPS3, Cr2Ge2Te6, Cr2S3, CrBr3, CrCl3, CrGeTe3, CrPS4, CrSeBr, CuCrP2S6, CuIn7Se 11、FeCl2、FePS3、FePSe3、MoTe2、GaGeTe、GaInS3、GaSeTe、GaS Se、GaPS4、GaSTe、GeAs、GeSe、GeS、GeS2、GeTe、HfSe2、HfS2、 HfTe2, In2S3, In2Se3, InSe, InTe, InGaSe2, InSeBr, InSnSe, MnPS3, MnPSe3, MoSSe, MoWSe2, MoWS2, MoWTe2, MoNbSe2, MoO2 2.5 Cl 0.5 、MoReS2、MoTaSe2、MoVSe2、Na2Co2TeO6、Nb2SiTe4、NbReS2、NbReSe2、NbS3、Ni2SiTe4、Ni3TeO6、NiCl 2、NiI2、NiPS3、PbI2、PbTe、PtTe2、ReMoS2、ReNbS2、ReNbSe2、ReSSe、SbAsS3、SbSe、SbSI、SiP、SnPSe3、 SnS、Ta2NiS5、TaS2、TaS3、TaSe2、TaWSe2、TlSe、TiBr3、SnTe2、TiS3、TlGaS2、TlGaSe2、TlGaTe2、TlIn S2, WTe2, WReSe2, ZrS2, ZnIn2S4, ZnPS3, ZnPSe3, ZrGeTe4, ZrS3, ZrSe2, ZrSe3, ZrTe2 rTe3、Cr2Si2Te6、Cr2Te3、CrI3、CrSBr、CrTe2、Fe3GeTe2、Fe4GeTe2、TaCo2Te2、VS2、VSe2、VTe2、BiSb TeSe, BiTe, CuFeTe, HfTe5, FeSe, FeTeSe, FeTe, NbS2, NbSe2, NbTe2, NbTe4, NiTe2, PdBi2, PdTe2, SnTa S2、TaTe2、TiTe2、Tl2Ba2CaCu2O8、ZrSiS、CdAs2、CuSi2P3、NbAs2、PbTaSe2、Ta2NiSe5、Ta2NiTe5、Ta2S e8I、TaNi2Te3、TiS2、TiSe2、WNbTe2、ZnAs2、ZrTe5、LaTe2、NbSe3、Bi2SeTe2、Bi2Te2S、BiInTe3、Bi2Se 1.5 Te 1.5 、Bi4Te 1.5 S 1.5GeBi2Te4, PbBi2Te4, SnBi4Te7, SnSb2Te4, NiTe, SbTe, SiTe2, BiTeI, InSSe, PbSnS2, TlGaS3, C3N4, Cu2Te, GeSeTe, MnTe, As2Se3, CrPS3, SnSe, WReS2, TiBr, BaTiS3, Al2O3, BiFeO3, Ag3AsS3, HgS, bismuth, strontium, calcium, copper oxides, black arsenic or black phosphorus.

[0067] For the liquid lens 1 to function properly, liquid media 5 and 6 should be frozen at the lowest achievable temperature. The crystallization temperature of this liquid lens 1 should be in the range of -20 to -50 degrees Celsius, preferably -35 degrees Celsius. This is achieved by using media with low crystallization temperatures, such as silicone oil with a freezing point below -60°C or a mixture of water (33.3%) and glycerol (66.7%) with a freezing point as low as -46.5°C.

[0068] The recommended liquid lens 1 operates as follows.

[0069] When no voltage is applied to electrode 3 and they do not form an electromagnetic field [ Figure 1 The liquid lens 1 is in its initial state (meniscus 4 is a plane) and has zero or near-zero optical power, meaning it functions as a plate with parallel surfaces and does not alter the path of light. When a voltage is applied to electrode 3... Figure 2 Furthermore, when used to generate an electromagnetic field, the conductive liquid medium (or a medium with magnetic nanoparticles) moves to the outer periphery of the liquid lens 1 under the influence of an electric field (or a magnetic field formed by an alternating voltage on electrode 3), thereby changing the radius of curvature of the meniscus 4 to a value R according to the linear dimensions of the capsule 2, including its thickness and light-transmitting diameter (aperture). Thus, the optical power of the liquid lens 1 changes: the higher the voltage applied to electrode 3, the greater the energy of the electromagnetic field they generate, the smaller the radius of curvature R (numerically), and the greater the optical power of the liquid lens 1.

[0070] The maximum optical power limit of the liquid lens 1 is caused by the refractive index difference of the liquid medium 5-6 and the minimum achievable radius of curvature R of the meniscus 4. In air, for a capsule 2 with a diameter d = 2 mm, a thickness H = 1 mm (i.e., the radius of curvature R of the meniscus 4 = 1 mm) and a refractive index difference Δn = 1.2, the optical power of the liquid lens 1 includes 1200 diopters. In the context of this application, the optical power of the liquid lens 1 described herein and hereinafter is understood as its maximum achievable value in air with the maximum voltage applied to the electrode 3 and the corresponding maximum electromagnetic field energy.

[0071] This expansion of the achievable power range (0 to 1000 diopters and above) produces unexpected technical effects—significantly expanding the possible applications of liquid lenses, especially when the proposed high-power liquid lens 1 is integrated into wearable optics devices, such as contact lenses or intraocular lenses, to form magnified images of objects within the field of vision, creating augmented reality, virtual reality, or extended reality (AR / VR / XR) for the prevention and treatment of myopia.

[0072] According to the first implementation scheme for achieving zoom function [ Figures 3-10 The contact lens 8 comprises only a power supply and control module 9 and a reconfigurable optical system in the form of a proposed liquid lens 1, which occupies at least a portion (preferably 30% to 60%) of the user's eye 11's field of vision 10. Electrodes 3 of the liquid lens 1 are connected to the power supply and control module 9. The liquid lens 1 is adapted to focus the image of the corresponding object 12 onto the lens 14 instead of the retina 13 of the eye 11, to achieve the so-called Maxwellian view (see "Maxwellian view," Gerald Westheimer, Visual Research, Vol. 6, Nos. 11-12, December 1966, pp. 669-682, doi:10.1016 / 0042-6989(66)90078-2). This scheme forms a clear, magnified image on the retina 13, resulting in a visible magnification of the object 12. The advantage of the Maxwell field of view is its wide field of view (FOV) and its ability to work with eyes that have defects such as myopia / hyperopia, as no vision correction is required. When the optical power of the liquid lens 1 is not less than 300 diopters, two times or more magnification of the object 12 can be obtained.

[0073] Figures 3-5 A contact lens 8 with a built-in liquid lens 1 is shown, which occupies the entire field of vision 10 (100% coverage).

[0074] When no voltage is applied to the electrodes 3 and they do not form an electromagnetic field, i.e., when the liquid lens 1 is not activated, the user's eye 11 has a standard vertical field of view 10 of approximately 60° (twice the angle of 120°). In this case, light rays projected onto the cornea 15 at an angle exceeding 60° (e.g., 70°) in the vertical plane will not hit the retina 13 after passing through the optical system of the eye 11 and therefore cannot be perceived by the user.

[0075] When a voltage is applied to the electrodes 3 and they are used to generate an electromagnetic field, i.e., when the liquid lens 1 is activated, it becomes an optical element with a specific optical power (250-500 diopters). In this case, due to the presence of the liquid lens 1, light rays projected onto the contact lens 8 from a distant object (at an angle of 0° with the optical axis of the eye) do not focus on the retina 13, but rather on the lens 14 (in this case, the lens is in a relaxed state). Due to the Maxwell field effect, these light rays will form a clear, magnified image on the retina 13. At the same time, light rays from a closer object 12, projected onto the optical axis at a certain angle (e.g., up to 25° – half an angle), are also focused on the lens 14, projecting a clear image onto the retina 13 and being imaged by the eye's optical system. Due to the high optical power of the liquid lens 1, light rays exceeding a critical angle (e.g., greater than 25°) are focused in front of the lens 14 and projected in a defocused state onto the outermost edge of the retina 13 or completely miss the retina 13, making them invisible to the user.

[0076] Using the following liquid lens parameters, optical magnification of 2-3x (preferably 2.4x) can be achieved across the entire field of view 10 (100% coverage):

[0077]

[0078]

[0079] The zoom effect of the liquid lens 1 in the contact lens 8 is stepwise rather than continuous, meaning there are actually two critical endpoints: liquid lens 1 is inactive (field of vision focused on retina 13) and liquid lens 1 is active (field of vision focused on lens 14). All intermediate states are inactive when the optical power of liquid lens 1 changes to focus on the area between lens 14 and retina 13, because in this state, the eye 11 cannot form a focused image on retina 13.

[0080] However, the optical power control of the liquid lens 1 can be used for another purpose. For example, in the example above, the lens 14 is in a relaxed state, i.e., focused at infinity. During eye accommodation, the posterior wall of the lens 14 changes its radius of curvature and optical power. This also means that light rays previously focused onto the lens 14 by the liquid lens 1 may now reach the retina 13 in a slightly defocused state because the posterior wall of the lens 14 has changed its position. By reducing the optical power of the liquid lens 1 according to the increase in the optical power of the lens 14, the changes made by the lens 14 to the optical system can be compensated, and a clear and sharp image can be achieved on the retina again through eye accommodation. Therefore, if an image magnified using the zoom function is blurred due to eye accommodation, this blurring can be compensated for by controlling the curvature of the meniscus 4, and the magnified image can be made clear and sharp again.

[0081] The contact lens 8 proposed according to the first embodiment cannot achieve zoom functionality across the entire field of vision 10, but only within a portion of it: for example, 50% of the central field of vision of the eye—this embodiment would have a more compact size. Figure 7 The diagram illustrates a contact lens 8 with a built-in liquid lens 1 when no voltage is applied to the electrode 3, i.e., when the liquid lens 1 has no optical power and operates as a plate with parallel surfaces. In this case, the eye 11 has a standard vertical field of view of ~60° (twice the angle of 120°), and light projected onto the cornea 15 at a greater angle does not reach the retina 13 after passing through the eye's optical system, and therefore cannot be imaged by the user's eye.

[0082] Figure 8 The same contact lens 8 with a voltage applied to electrode 3 is shown, i.e., when the liquid lens 1 has an optical power defined by the radius of curvature of the meniscus 4 (formed due to the presence of an electromagnetic field) and refractive indices n1 and n2. In this case, light rays projected onto the liquid lens 1 portion of the contact lens 8 from infinity (angle 0°) are not focused on the retina 13, but rather on the lens 14, which is in a relaxed state. Due to the Maxwell field effect, these rays will form a sharp image on the retina 13. Similarly, all light rays projected onto the liquid lens 1 at specific angles (e.g., up to 25° – half an angle) are also focused on the lens 14 and projected onto the retina 13 in a sharp state, and imaged by the optical system of the eye 11. Due to the high optical power of the liquid lens 1, light rays projected onto the liquid lens 1 at larger angles (e.g., greater than 25°) are focused in front of the lens 14. Therefore, they are projected in a defocused state onto the outermost edge of the retina 13, or completely miss the retina 13, and thus cannot be imaged by the user's eye 11.

[0083] Furthermore, there is light projected onto the peripheral portion of the contact lens 8 that is not covered by the liquid lens 1. This light passes through the contact lens 8 unchanged (if the contact lens 8 itself has 0 diopter) and is focused onto the retina 13 in a conventional manner by the lens 14. Therefore, within the visual field 10, a central portion with a magnified image of the object 12 and a reduced viewing angle (e.g., from 120° to 50° – full vertical angle) is formed, as well as a normal peripheral portion with a viewing angle containing a normal-sized image of the object 12. Figure 10 ].

[0084] To achieve 2-3x optical magnification (preferably 2.4x) within 50% of the central field of view, the liquid lens 1 should have the following parameters:

[0085]

[0086] According to the second implementation scheme for realizing AR / VR / XR functions [ Figures 11-14 The contact lens 8 includes a display 16, a power supply and control module 9, and an optical system in the form of a liquid lens 1 disposed between the display 16 and the eye 11. Electrodes 3 of the liquid lens 1 are connected to the power supply and control module 9, and the optical power of the liquid lens includes at least 800 diopters. In this configuration, the liquid lens 1 is able to focus the emission from the display 16 screen onto the lens 14 of the user's eye to achieve a Maxwell field of view, because the distance from the image source (focal plane) to the liquid lens 1 is much smaller than the distance from the liquid lens 1 to the retina 13 (image plane). This configuration allows for the formation of a clear, aberration-free image of the display 16 on the retina 13, with high transmittance and a wide field of view, superimposed onto the real scene.

[0087] The image source represents a display 16 based on a light-emitting diode matrix (LED, micro-LED, OLED, etc.). The size of the display 16 can be from 50×50 to 500×500μm, preferably 100×100μm, and the pixel size can be up to 1μm. Alternatively, the display can have any other shape, such as a rectangle or circle with a diameter of 50, 100, or 500μm, and the pixels are arranged in a honeycomb pattern (hexagons). In this case, the size of the display 16 described in this application is understood as the maximum linear size: the diagonal of a square or rectangle, the diameter of a circle, the distance between opposite vertices of a hexagon, etc.

[0088] The display 16 is attached to the outer surface of the contact lens 8 and faces the pupil of the user's eye. The display 16 is powered by a power and control module 9, which may include a rechargeable battery and / or an inductor coil built into the contact lens 8.

[0089] To ensure that the display 16 is located in or near the focal plane, the distance along the optical axis between the display and the liquid lens 1 should be 50-250 μm, preferably 100 μm. The corresponding gap 17 can be formed by a hollow chamber 18 filled with air (n=1) or by a layer of polymer material (PMMA or other material transparent in the visible spectrum).

[0090] An embodiment with air gap 17 is as follows Figure 11 As shown. In this case, the entire projection optics system represents a hollow chamber 18, made of plastic, polymer, glass, crystal, nano-glass ceramic, or other materials transparent in the visible spectrum, containing a display 16 mounted on one side and a liquid lens 1 mounted on the other side. In this case, the gap 17 between the display 16 and the liquid lens 1 is filled with air or other gas. This projector structure is installed in the contact lens 8 as follows: on the main polymer layer of the contact lens 8 (closest to the cornea 15), at the center, the chamber 18 is installed together with the display 16 and the liquid lens 1, and then all the necessary electronics (power and control module 9 with inductor coils, rechargeable battery, power conductors, and control electrodes 3 of the liquid lens 1) are installed on its periphery. The periphery is covered with polymer and polymerized to fix the chamber 18, followed by the application of a finishing polymer layer (farthest from the cornea 15). For a liquid lens 1 with a light transmission diameter (aperture) of 160 μm and a thickness of 40 μm, the gap 17 should be 100 μm.

[0091] Figure 12An alternative embodiment of a projection system with a gap 17 formed by a layer of polymer material is shown. This projector structure is mounted into a contact lens 8 as follows: On the main polymer layer of the contact lens 8 (closest to the cornea 15), at the center, a liquid lens 1 (thinner than the entire projection system with chamber 18 described above) is mounted; then, on the outer periphery, all necessary electronics (a power and control module 9 with an inductor coil, rechargeable battery, power conductor, and control electrodes 3 of the liquid lens 1) are mounted, the periphery is covered and polymerized with polymer; subsequently, an intermediate polymer layer with gap 17 is applied; a display 16 is mounted at the center and connected to the power and control module 9; and then a finishing polymer layer (farthest from the cornea 15) is applied. The difference in this case is that the air gap 17 (n=1) between the display 16 and the liquid lens 1 is replaced by a gap 17 formed by polymer layers (n=1.2-1.4), which may negatively impact the overall optical system dimensions along the optical axis—the system must be slightly thicker than in the former case. However, although the display 16 exhibits a very wide light divergence in air (spatial angle 140-180 degrees), within the polymer layer, according to Snell's law, the light divergence can be significantly reduced (the higher the refractive index of the polymer, the lower the light divergence from the display 16). For example, when using a polymer with a refractive index of ~1.5 in the visible spectrum, the light divergence of the display can be reduced from 140-180 degrees to 75-90 degrees. The divergence angle of the display 16 needs to be reduced in order to reduce the entrance aperture (transmitting diameter) of the liquid lens 1, thereby reducing its minimum overall size along the optical axis. For a liquid lens 1 with a transmitting diameter (aperture) of 500 μm and a thickness of 200 μm, the gap 17 should contain 150 μm.

[0092] The working method of the contact lens 8 according to the second implementation plan is as follows.

[0093] When the display 16 is activated, the display screen forms a diverging light beam, which is collected by the liquid lens 2 and focused onto the user's lens 14. This beam is focused by controlling the curvature of the meniscus 4 of the liquid lens 1 using an electromagnetic field formed by the electrodes 3. Therefore, image aberrations are prevented, taking into account the user's visual impairment (myopia or hyperopia), and a wide field of view—up to 100° (full angle)—is formed. At this time, a magnified, clear, and sharp image of the display 16 is formed on the retina 13.

[0094] According to the third implementation plan for achieving the function of preventing and treating myopia [ Figures 15-17The contact lens 8 includes one or more light-emitting diodes 19 (e.g., LEDs) facing the user's eye 11, a power supply and control module 9, and an optical system in the form of a liquid lens 1 disposed between each LED 19 and the eye 11. The electrodes 3 of the LEDs 19 and the liquid lens 1 are powered and controlled by a similar power supply and control module 9, which may include a rechargeable battery and / or an inductor coil built into the contact lens 8. To avoid overlapping with the central portion of the pupil and interfering with normal vision, the LEDs 19 (preferably 2 to 40 diodes) are located on the outer periphery of the contact lens 8, for example, 5-10 mm from its optical axis.

[0095] In this embodiment, the liquid lens 1 should provide the ability to focus the emission from the light-emitting diode 19 in front of the retina 13 of the user's eye 11. During operation, based on signals from the control electrode 3, the liquid lens 1 can change the curvature of the meniscus 4, thereby focusing the stimulus from the light-emitting diode 19 at different distances from the retina 13. At this time, the degree of defocus of the emitted light spot from the light-emitting diode 19 on the retina 13 can change in real time and should include 0.5 to 10 diopters, preferably 2 to 6 diopters. Therefore, the optical power of the liquid lens 1 is preferably not less than 1000 diopters.

[0096] The working method of the contact lens 8 according to the third implementation plan is as follows.

[0097] According to the control signal, the light-emitting diode 19 and the electrode 3 of the liquid lens 1 are periodically powered by the module 9. When using the liquid lens 1 with a light-transmitting diameter (aperture) of 1 mm and a thickness of 0.2 mm, a 1×1 μm blurred image of the light-emitting diode 19 located 0.7 mm away from the liquid lens is formed on the retina 13. For an eye 11 with a longitudinal dimension of 24 mm (distance from the cornea 15 to the retina 13), the radius of curvature R of the meniscus 4 = 1.34 mm corresponds to a myopic defocus D = 2 diopters, while the radius of curvature R = 1.33 mm corresponds to a myopic defocus D = 6 diopters. Since the user's eye 11 can have different longitudinal dimensions, the use of the reconfigurable liquid lens 1 makes this contact lens 8 with myopia prevention and treatment functions very flexible in use, because the desired degree of defocus of the stimulus can be set by controlling the curvature of the liquid lens 1. Furthermore, the contact lens 8 disclosed according to the third embodiment enables a significant expansion of the possible range of therapeutic interventions by providing the possibility of gradually changing the degree of defocus of the light-emitting diode 19 image formed on the user's retina.

[0098] The disclosed intraocular device [ Figures 18-24The device includes an intraocular lens comprising a liquid lens 1, a holding element 20 that holds the intraocular lens within the user's eye, and a power supply and control module 9. The power supply and control module 9 is configured to convert the user's control signals into energy from an electromagnetic field formed by control electrodes 3, and to change the optical power of the liquid lens 1. Thus, the disclosed intraocular device can adjust according to the user's control signals, similar to the activity of a natural lens.

[0099] As described in the previous embodiments, the inlet and outlet windows (walls) of the capsule 2 of the liquid lens 1 should be made of a material that is transparent in the visible spectrum. When used as an intraocular lens, the capsule 2 is preferably made of a biocompatible elastic polymer material for easy implantation into the eye 11.

[0100] As one implantation option, the surgeon implants a tubular intraocular liquid lens 1 into the user's eye 11 through a micro-incision on the cornea 15. Inside the eye, the liquid lens 1 unfolds and is secured by a specific retaining element 20. This retaining element 20 can be implemented as two or more independent tabs made of an elastic polymer material. Figures 18-19 ], or realized as a casting integrally formed with capsule 2 [ Figure 20 The element 20 is at an angle of 3-10 degrees (preferably 4-7 degrees) to the plane perpendicular to the optical axis.

[0101] There are two options for implanting the disclosed intraocular device: either the anterior chamber or the posterior chamber of the user's eye. When implanted in the anterior chamber... Figure 21 The element 20 unfolds and is fixed between the cornea 15 and the iris. When implanted in the posterior chamber... Figures 22-24 The element 20 unfolds and is fixed between the iris and the ciliary body—a more natural position because that is where the removed lens is located.

[0102] The optical power of the human lens is known to be in the range of 19-33 diopters. When relaxed, the lens has an optical power of 19 diopters, capable of focusing light from a distant object (at an assumed infinity). To adjust to infinity, the liquid lens 1 should also be adapted to form an optical power of 19 diopters, corresponding to the specific curvature of the meniscus 4. Figure 22 For a liquid lens 1 with a diameter of 10 mm, a thickness of 1 mm, a first liquid medium refractive index n1 = 1.33 (the standard value for water), and a second liquid medium refractive index n2 = 3.0, an optical power of 19 diopters is achieved by the radius of curvature R = 88 mm of the meniscus 4. To generate the electromagnetic field providing this curvature, the electrode 3 should be subjected to a corresponding voltage when the power supply and control module 9 sends a signal. In this case, the intraocular device is an analogue to the natural lens in a relaxed state.

[0103] The human lens, under maximum tension, has a diopter of 33, enabling it to focus light from an object located nearby, the so-called "near point," onto the retina 13. The near point is the minimum distance from the target object to the eye 11 (more specifically, its cornea 15) that the eye can focus on. This distance depends on the individual, their age, and health condition, but should not be less than 70-80 mm. To focus at the near point, the liquid lens 1 in the disclosed intraocular device should also have a diopter of 33, corresponding to different radii of curvature of the meniscus 4. Figure 23 For the same liquid lens with a diameter of 10 mm, a thickness of 1 mm, n1 = 1.33 and n2 = 3.0, an optical power of 33 diopters is achieved at the radius of curvature R = 51 mm of the meniscus 4. To provide this curvature of the meniscus 4, the electrode 3 should form an electromagnetic field with energy higher than that used for 19 diopters, i.e., the voltage on the electrode should be higher.

[0104] Although the normal human lens cannot physically focus on a point closer than 70-80 mm to the cornea, the disclosed intraocular device can do so because the adjustment range of the liquid lens 1 is not exhausted. Therefore, the liquid lens 1 can change its optical power to higher values, up to 200 diopters, meaning it can focus on a closer point. For example, the same liquid lens with a diameter of 10 mm, a thickness of 1 mm, n1 = 1.33, n2 = 3.0, an optical power of 128 diopters, and a radius of curvature R of the meniscus 4 of 13 mm can focus on an object 12 at a distance of 158.2 mm from the cornea. Figure 24 ].

[0105] Therefore, the disclosed intraocular device extends the capabilities of the human eye, enabling it to examine objects from very close distances, essentially analogous to macro lenses in photography or microscope lenses with specific magnification. In this case, the angular resolution (containing 1-1.5 degrees in the central region of a healthy human eye) will depend on the surface quality of the liquid lens 1, the surface curvature of the capsule 2, and other conditions.

[0106] When examining an object 12 at such close range, especially when it is opaque, problems may arise due to the low brightness of such an object 12. Eyebrows, brow ridges, eyelashes, cheeks, nose, and other parts of the user's head may block natural light from the environment from reaching the object 12 at such close range and prevent scattered light from the object 12 from reflecting into the eye 11. This problem can be solved, for example, by using a contact lens 8 with one or more built-in light-emitting diodes 19 facing away from the eye 11. Such light-emitting diodes 19 illuminate the object 12 at such close range and can be connected to a similar power and control module 9, which may contain a rechargeable battery and / or inductor coil, solar cell, ASIC chip, etc., built into the contact lens 8. The light-emitting diodes 19 are preferably positioned on the outer periphery of the contact lens 8, outside the eye's field of vision and pupil diameter, for example, at a radius of 6-9 mm from the lens optical axis. In this embodiment, the power supply and control module 9 of the liquid lens 1 shall be configured to send an activation signal to the light-emitting diode 19 (through the power supply and control module 9 of the contact lens 8) when the optical power of the liquid lens 1 exceeds 35 diopters.

[0107] The working principle of the disclosed intraocular device is as follows.

[0108] During the eye's accommodation of an external object 12, the brain sends signals in the form of electrical signals transmitted through ganglia to the ciliary muscle of the eye 11, forcing the muscle to contract and relax (the ciliary muscle remains in place when the lens is removed). When attempting to focus, the ciliary muscle contracts, and the user's control signal is converted by the power supply and control module 9 of the liquid lens 1 into energy of an electromagnetic field formed by electrodes 3 (e.g., by converting ciliary muscle pressure into an electrical signal using a piezoelectric element integrated into the lug 20 and an amplitude amplifier that amplifies the signal from the piezoelectric element). Changes in electromagnetic field energy result in changes in the curvature of the meniscus 4, and correspondingly, changes in the optical power of the liquid lens 1. When the optical power of the liquid lens 1 exceeds 35 diopters, the light-emitting diode 19 automatically turns on to illuminate the object 12.

[0109] Therefore, the use of the disclosed colloidal solution containing nanoparticles and the resulting increased refractive index difference of the liquid medium, thereby increasing the achievable range of optical power, significantly expands the possible application areas of the lens and enables the realization of the disclosed implementation schemes for contact lenses and intraocular devices.

Claims

1. A liquid lens, implemented as a capsule, comprising an immiscible first liquid medium having a refractive index n1 and a second liquid medium having a refractive index n2 such that n2 > n1, and a control electrode, wherein one of the liquid media is adapted to be controlled by an electromagnetic field via the electrode, characterized in that... The second liquid medium represents a colloidal system formed of a liquid and solid high-refractive-index nanoparticles, wherein the refractive index of the nanoparticles is higher than that of the liquid, and wherein the first liquid medium and the second liquid medium are preferably implemented such that their refractive index difference Δn = n2 - n1 > 1.

5.

2. The liquid lens according to claim 1, characterized in that, The high refractive index nanoparticles are composed of TiO2, GaP, AlSb, GaSb, InSb, AlAs, GaAs, InAs, SiC, TiC, VC, Fe2O3, InP, PbSe, ZnSe, CdS, CuGaS2, CdTe, Te, ZnTe, and Bi4Ti3O. 12 It is made of PbTiO3.

3. The liquid lens according to claim 1, characterized in that, The high-refractive-index nanoparticles are made of van der Waals material, which consists of two-dimensional layers bonded together by van der Waals forces.

4. The liquid lens according to claim 3, characterized in that, The van der Waals material is MoS2, MoSe2, WSe2, Cd3As2, Mo2Ga2C, Nb2AlC, Ti2AlC, SnS2, SnSe2, ReS2, ReSe2, GaSe, PdS2, PdSe2, PtS2, PtSe2, or GaS.

5. A contact lens comprising a power supply and control module and a reconfigurable optical system, characterized in that, The optical system is equipped with the liquid lens of claim 1, the liquid lens occupying at least a portion of the user's field of vision and adapted to focus images of objects located within the field of vision onto the user's lens and provide visible magnification of these objects.

6. The contact lens according to claim 5, characterized in that, The optical power of the liquid lens includes not less than 300 diopters and is capable of magnifying objects within the field of view by at least two times.

7. The contact lens according to claim 5, characterized in that, The liquid lens occupies 30% to 60% of the field of view.

8. A contact lens comprising a display with its screen facing the user's eyes, a power supply and a control module, and an optical system disposed between the display and the eye, characterized in that, The optical system is equipped with a liquid lens as described in claim 1, the liquid lens being adapted to focus emissions from the screen onto the user's lens.

9. The contact lens according to claim 8, characterized in that, The optical power of the liquid lens includes not less than 800 diopters.

10. The contact lens according to claim 8, characterized in that, The liquid lens is mounted with a gap relative to the screen.

11. The contact lens according to claim 10, characterized in that, The gap is formed by a hollow cavity.

12. The contact lens according to claim 10, characterized in that, The gap is formed by a layer of polymer material.

13. A contact lens comprising at least one light-emitting diode disposed on the outer periphery of the contact lens and facing the user's eye, a power supply and a control module, and an optical system disposed between the light-emitting diode and the eye, characterized in that, The optical system is equipped with the liquid lens of claim 1, the liquid lens being adapted to focus the emission from the light-emitting diode in front of the user's retina.

14. The contact lens according to claim 13, characterized in that, The optical power of the liquid lens includes not less than 1000 diopters.

15. The contact lens according to claim 13, characterized in that, The liquid lens is adapted to change the degree of defocus of the light-emitting diode's emission onto the user's retina within a range of 0.5 to 10 diopters.

16. The contact lens according to claim 13, characterized in that, It has 2 to 40 light-emitting diodes disposed on the outer periphery of the contact lens.

17. An intraocular device comprising an intraocular lens adapted to be adjusted according to a user control signal, and a holding element for fixing the intraocular lens in the user's eye, characterized in that, The intraocular lens is equipped with the liquid lens and power supply and control module as described in claim 1, wherein the control module is configured to convert the user's control signal into energy of an electromagnetic field formed by the control electrodes of the liquid lens.

18. The intraocular device according to claim 17, characterized in that, The power supply and control module is configured to change the optical power of the liquid lens from at least 19 diopters to 33 diopters.

19. The intraocular device according to claim 18, characterized in that, The power supply and control module is configured to change the optical power of the liquid lens up to 200 diopters.

20. The intraocular device according to claim 19, characterized in that, The power supply and control module is configured to send an activation signal to the light-emitting diode in the contact lens when the optical power of the liquid lens exceeds 35 diopters.

21. The intraocular device according to claim 17, characterized in that, The liquid lens capsule is made of an elastic polymer material.

22. The intraocular device according to claim 21, characterized in that, The retaining element is integrally formed with the liquid lens capsule.

23. The intraocular device according to claim 17, characterized in that, The retaining element is implemented as a lug made of an elastic polymer material.

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