阅读说明：本技术 植入到患者眼前房中的眼科组件及调节患者视力的方法 (Ophthalmic component for implantation into the anterior chamber of a patient's eye and method of modulating the vision of a patient ) 是由 马克斯·布瓦赛 亚历山大·帕斯卡雷拉 朱利安·雅科 于 2019-01-15 设计创作，主要内容包括：本发明涉及一种用于植入到患者眼前房中以向该患者提供视力调节的眼科组件。眼科组件包括变焦式透镜(11)和用于改变变焦式透镜(11)的焦距的致动器(12)。眼科组件包括被配置为确定患者眼所注视的物体的距离参数的自动聚焦系统(13)；被设置为将距离参数转换为变焦式透镜(11)的焦距值的信号处理单元(14)；以及被配置为根据从信号处理单元(14)接收的焦距值来控制致动器(12)的致动器控制单元(15)。本发明还涉及一种通过植入到患者眼前房中的眼科组件来调节该患者的视力的方法,该眼科组件(10)包括变焦式透镜(11)、致动器(12)、自动聚焦系统(13)、信号处理单元(14)、致动器控制单元(15)和电源(16)。该方法包括以下步骤。自动聚焦系统(13)确定与患者眼注视的物体有关的距离参数；将距离参数的值发送到信号处理单元(14)；信号处理单元(14)将离参数转换为变焦式透镜(11)的焦距；将变焦式透镜(11)的焦距发送给致动器的控制单元(15)；以及致动器控制单元(15)控制致动器(12)使得变焦式透镜(11)的焦距对应于从信号处理单元(14)接收的焦距值。(The present invention relates to an ophthalmic assembly for implantation into the anterior chamber of the eye of a patient to provide vision accommodation to the patient. The ophthalmic assembly comprises a variable focus lens (11) and an actuator (12) for changing the focal length of the variable focus lens (11). The ophthalmic component comprises an auto-focusing system (13) configured to determine a distance parameter of an object at which the eye of the patient is gazed; a signal processing unit (14) arranged to convert the distance parameter into a focal length value of the zoom lens (11); and an actuator control unit (15) configured to control the actuator (12) in accordance with the focus value received from the signal processing unit (14). The invention also relates to a method of adjusting the vision of a patient by means of an ophthalmic assembly implanted in the anterior chamber of the eye of the patient, the ophthalmic assembly (10) comprising a variable focus lens (11), an actuator (12), an autofocus system (13), a signal processing unit (14), an actuator control unit (15) and a power supply (16). The method comprises the following steps. An autofocus system (13) determines a distance parameter relating to an object at which the eyes of the patient are fixated; sending the value of the distance parameter to a signal processing unit (14); the signal processing unit (14) converts the discrete parameters into the focal length of the zoom lens (11); a control unit (15) for transmitting the focal length of the zoom lens (11) to the actuator; and an actuator control unit (15) controls the actuator (12) such that the focal length of the zoom lens (11) corresponds to the focal length value received from the signal processing unit (14).)

1. An ophthalmic component (10) for implantation into the anterior chamber of the eye of a user, the ophthalmic component comprising a support (17) on which is provided:

A zoom lens (11) having a variable diopter;

an auto-focus system (13) configured to receive light from a target object at which the user is gazing and to determine a distance parameter of the target object;

a processor (14, 15) configured to convert the distance parameter into a control value;

an actuator (12) configured to vary the diopter strength of the variable focus lens in accordance with the control value; and

at least one power source for powering various components of the ophthalmic assembly,

the method is characterized in that:

the autofocus system (13) comprises:

an auto-focus lens system (27, 28a, 28b, … …, 28n) positioned on the support proximate to the zoom lens; and

at least one autofocus sensor (26) configured to measure a contrast value of at least a portion of an image formed on at least a portion of the autofocus sensor by light passing through the autofocus lens system,

the auto-focus lens system is configured to cause light from the target object at which the user is looking that passes through at least a portion of the auto-focus lens system to form an image on a portion of the auto-focus sensor that produces a maximum contrast at which to measure, the auto-focus system being configured to determine the distance parameter using a parameter of the auto-focus lens system at which the maximum contrast is measured and to send the distance parameter to the processor.

2. The ophthalmic assembly of claim 1, wherein the autofocus lens system comprises an autofocus lens, a distance of the autofocus lens from the autofocus sensor is adjustable, the autofocus system is configured to adjust the distance between the autofocus lens and the autofocus sensor until a focus distance at which the maximum contrast is measured is reached, and to use the focus distance as the distance parameter.

3. The ophthalmic assembly of claim 1, wherein the autofocus lens system comprises a variable focus autofocus lens with adjustable focal length, the autofocus system being configured to vary the focal length of the autofocus lens until a focal length at which the maximum contrast is measured is reached, and to use the focal length as the distance parameter.

4. An ophthalmic assembly according to any preceding claim comprising a plurality of the autofocus lens systems each disposed on the support at a different position proximate the variable focus lens.

5. The ophthalmic assembly of claim 1, wherein the autofocus lens system includes a plurality of microlenses each having a different fixed focal length, the autofocus sensor having a plurality of zones in one-to-one correspondence with the microlenses, each zone for receiving an image of the target object from light passing through the corresponding microlens, the autofocus system configured to use the focal length of the microlens where the image has the maximum contrast as the distance parameter.

6. The ophthalmic assembly of claim 1, wherein the autofocus lens system includes a plurality of microlenses each having a different fixed focal length, the autofocus system further including a plurality of the autofocus sensors each configured to receive an image of the target object from light passing through the corresponding microlens, the autofocus system configured to use the focal length of the microlens where the image has the maximum contrast as the distance parameter.

7. The ophthalmic assembly of claim 5 or 6, wherein the autofocus system is further configured to infer an extrapolated focal length from two adjacent microlenses where the image is close to the maximum contrast, and use the extrapolated focal length as the distance parameter.

8. An ophthalmic assembly according to any preceding claim wherein the variable focus lens is a lens comprising at least one element having a deformable shape, the actuator being configured to change the shape of the element in dependence on the control value, thereby changing the refractive power of the variable focus lens.

9. An ophthalmic assembly according to claim 8, wherein the variable focus lens comprises two immiscible liquids of different refractive indices, one of the liquids being electrically conductive and the other being electrically insulating, the two liquids being separated by an interface forming a meniscus, the meniscus being the element having a deformable shape, the actuator being configured to vary the potential difference between the two liquids in dependence on the control value, thereby varying the shape of the meniscus to vary the focal length of the variable focus lens.

10. An ophthalmic assembly according to claim 8, wherein the variable focus lens (11) comprises an impermeable elastomeric membrane and the actuator comprises at least one movable compression element (21) arranged on the support at the periphery of the variable focus lens, the actuator being configured to move the compression element to cause a deformation of the shape of the membrane to change the optical power of the variable focus lens.

11. An ophthalmic assembly according to claim 8, wherein the variable focus lens (11) comprises an impermeable elastomeric membrane and contains at least one liquid (23) originating from a reservoir (24), the actuator comprising a pump (25) configured to vary the amount of the liquid contained in the lens in accordance with the control value so as to controllably deform the membrane, thereby varying the optical power of the variable focus lens.

12. An ophthalmic component according to any one of claims 1 to 7, wherein the variable focus lens comprises regions containing liquid crystals whose refractive index varies in dependence on an electric field applied to them, the actuator being configured to control the electric field applied to the liquid crystals.

13. An ophthalmic component kit for implantation into the two anterior chambers of two eyes of a user, the ophthalmic component kit comprising two ophthalmic components according to any preceding claim, one for each eye, each ophthalmic component further comprising means for communicating with the other ophthalmic component.

14. A method for adjusting the vision of a user by means of an ophthalmic component implanted in the anterior chamber of the eye of said user, said ophthalmic component (10) comprising a support (17) on which there is provided:

a zoom lens (11) having a variable diopter;

an auto-focus system (13) configured to receive light from a target object at which the user is gazing and to determine a distance parameter of the target object;

a processor (14, 15) configured to convert the distance parameter into a control value;

An actuator (12) configured to vary the diopter strength of the variable focus lens in accordance with the control value; and

at least one power source for powering various components of the ophthalmic assembly,

wherein the autofocus system (13) comprises:

an auto-focus lens system (27, 28a, 28b, … …, 28n) positioned on the support proximate to the zoom lens; and

at least one autofocus sensor (26) configured to measure a contrast value of at least a portion of an image formed on at least a portion of the autofocus sensor by light passing through the autofocus lens system,

the method comprises the following steps:

determining a distance parameter for the target object using the autofocus system;

converting, using the processor, the distance parameter to a control value; and

adjusting the diopter scale of the variable focus lens using the actuator, the adjustment based on the control value.

15. The method of claim 14, wherein determining the distance parameter comprises:

measuring, using the autofocus sensor, a maximum contrast value of an image formed on at least a portion of the autofocus sensor by light passing through the autofocus lens system;

Using a parameter of the auto-focus lens system when the maximum contrast is measured as the distance parameter; and

and sending the distance parameter to the processor.

Technical Field

The present invention relates to an ophthalmic assembly for implantation into the anterior chamber of the eye of a patient for providing vision accommodation to the patient. The ophthalmic assembly includes a variable focus lens and an actuator for changing a focal length of the variable focus lens.

The invention also relates to a method for adjusting the vision of a patient by means of an ophthalmic assembly implanted in the anterior chamber of the eye of the patient, the ophthalmic assembly comprising a zoom lens, an actuator, an autofocus system, a signal processing unit, an actuator control unit and a power supply.

Background

Currently, many people undergo cataract surgery. During such surgery, the diseased, opacified lens is removed and replaced with an artificial lens.

An inherent side effect of any cataract surgery is the loss of accommodation in the patient. The lens is usually replaced by a posterior chamber intraocular lens, which results in the simultaneous removal of accommodation functions that are critical for good vision at different distances. The result is that patients undergoing cataract surgery must wear glasses to obtain good vision at any distance.

In phakic eyes, i.e., eyes without the natural lens removed, age-related presbyopia, which causes a reduction in the accommodative ability of the natural lens, also causes problems due to loss of accommodation. Thus, the patient also relies on glasses and possibly progressive glasses.

Several artificial lenses have been developed to recreate the accommodation function or pseudo-accommodation function and to break away from the dependency on the glasses. Such lenses are, for example, multifocal lenses, lenses with an enlarged depth of focus or accommodating lenses. Each of these optical or mechanical methods has its own purposes and characteristics, but they may have some drawbacks. In particular, any method based on optical elements on the lens surface will eventually utilize a certain amount of light intensity. Such light intensities will have more or less energy losses for each allocation of a viewing distance and have more or less adverse effects, such as halos, glare or ghosts.

To overcome the above disadvantages, accommodative lenses have been developed. Currently, most of these accommodative lenses are based on mechanical motion. These accommodative lenses to be placed in the capsular bag of a patient's eye are designed to be actuated by the ciliary muscle to move the multi-lens optical system or to change the radius of curvature of the optical elements. A key problem with this approach is that the ciliary muscle can lose function with age due to previous conditions (cataracts, presbyopia, etc.). This diminished ciliary muscle contraction and the effects associated with cystic fibrosis generally do not allow sufficient movement to be provided to compensate for the intended level of accommodation.

Other accommodating lenses are not based on mechanical movement but on displacement of the liquid. The lens is formed by a cylindrical fluid chamber containing two immiscible fluids in contact with each other across a concave and convex surface and having different refractive indices. One of the fluids is in contact with two electrodes. A change in the voltage between the two electrodes changes the shape of the meniscus and thus the focal length of the lens.

Such lenses have some disadvantages. In particular, it is used for treating visual disorders in patients. This means that, depending on the extent of the obstruction, the width of the lens must be very large to cover a large obstruction range. In the case where the degree of the obstacle is severe, a case may occur in which the obstacle cannot be corrected by such a lens.

Due to the shape and size of the lens, it must be placed in the posterior chamber of the patient's eye. This means that the lens periphery receives little light depending on the size of the iris. This is a serious drawback in the case of a lens periphery for accommodating peripheral equipment. Moreover, this technique requires a large amount of energy, which does not match the constraints associated with the small available size.

Disclosure of Invention

It is an object of the present invention to overcome the disadvantages of prior art ophthalmic assemblies by providing an assembly that adjusts the vision of a patient without the need to wear eyeglasses. In addition, accommodation can be made for persons who lose their ciliary muscle contractility, particularly due to age or disease of the individual. The ophthalmic assembly is compatible with existing artificial lenses implanted to correct a patient's vision.

According to a first aspect, there is provided an ophthalmic component for implantation into the anterior chamber of an eye of a user, the ophthalmic component comprising a support on which is disposed:

a variable power lens having a variable diopter;

an auto-focus system configured to receive light from a target object at which a user is gazing and to determine a distance parameter of the target object;

a processor configured to convert the distance parameter into a control value;

an actuator configured to vary a diopter of the zoom lens according to a control value; and

at least one power source for powering various components of the ophthalmic assembly,

the method is characterized in that:

the auto-focusing system includes:

an auto-focus lens system positioned on the support portion to be close to the zoom lens; and

at least one autofocus sensor configured to measure a contrast value of at least a portion of an image formed on at least a portion of the autofocus sensor by light passing through the autofocus lens system,

the autofocus lens system is configured to cause light from a target object at which a user is looking that passes through at least a portion of the autofocus lens system to form an image on a portion of the autofocus sensor that produces a maximum contrast ratio at which a measurement is to be taken, the autofocus system being configured to determine a distance parameter using a parameter of the autofocus lens system at which the maximum contrast ratio is measured and send the distance parameter to the processor.

According to a second aspect, there is also provided an ophthalmic component kit for implantation in the two anterior chambers of two eyes of a user, the ophthalmic component kit comprising two ophthalmic components according to the preceding aspect, one for each eye, each ophthalmic component further comprising means for communicating with the other ophthalmic component.

According to a third aspect, a method is disclosed for adjusting a user's vision through an ophthalmic component implanted in the user's anterior chamber, the ophthalmic component comprising a support on which is provided:

a variable power lens having a variable diopter;

an auto-focus system configured to receive light from a target object at which a user is gazing and to determine a distance parameter of the target object;

a processor configured to convert the distance parameter into a control value;

an actuator configured to vary a diopter of the zoom lens according to a control value; and

at least one power source for powering various components of the ophthalmic assembly,

wherein the auto-focusing system comprises:

an auto-focus lens system positioned on the support portion to be close to the zoom lens; and

at least one autofocus sensor configured to measure a contrast value of at least a portion of an image formed on at least a portion of the autofocus sensor by light passing through the autofocus lens system, the method comprising:

Determining a distance parameter of the target object using an auto-focus system;

converting, using a processor, the distance parameter to a control value; and

adjusting the diopter of the zoom lens using an actuator, the adjusting based on the control value.

According to the present invention, a patient having an ophthalmic component implanted therein may have a similar accommodative function as that of a normal, healthy eye. The ophthalmic assembly may be applied to patients who have lost accommodation due to cataracts, for example. The ophthalmic assembly may also be implanted in the eye of a patient who has lost accommodation due to, for example, age, but retains his lens. In both cases, the ophthalmic component is capable of restoring the accommodative function of the user's eye.

During the implantation procedure of the artificial lens, the optical and geometrical characteristics of the lens implanted for the replacement lens are calculated, in particular on the basis of the correction to be made to the patient's vision and the geometrical characteristics of the patient's eye. The size and position of the lens is then determined based on these parameters. Implanted lenses are not always perfectly suited for use in patients because of the difficulty in making very accurate measurements of the characteristics of the eye, because the lens may move slightly within the eye, and because the characteristics of the patient's eye may change over time. An ophthalmic assembly according to the present invention can correct for the differences between the best theoretical lens and the lens actually implanted in the patient's eye to achieve normal vision. Furthermore, since the ophthalmic module restores the patient's accommodative function, the patient may not use glasses regardless of the viewing distance.

Drawings

The invention and its advantages will be better understood by reference to the drawings and detailed description of specific embodiments, in which:

figure 1 shows an ophthalmic component according to the invention;

figure 2 shows an ophthalmic assembly implanted in a patient's eye;

figure 3 is a schematic view of a first embodiment of a lens for use in an ophthalmic assembly according to the invention, in a first configuration;

figure 4 shows the lens of figure 3 in a second configuration;

figure 5 shows the lens of figures 3 and 4 in a third configuration;

figure 6 is a schematic view of a second embodiment of a lens for use in an ophthalmic assembly according to the invention, in a first configuration;

figure 7 shows the lens of figure 6 in a second configuration;

figure 8 shows a portion of a particular embodiment of an ophthalmic component according to the invention; and is

Figure 9 shows a possible shape of the ophthalmic component of the invention.

Detailed Description

Referring to the drawings and in particular to fig. 1, an ophthalmic assembly 10 according to the present invention comprises a zoom lens 11, an actuator 12, an autofocus system 13, a signal processing unit 14, an actuator control unit 15, a power supply 16 and a support 17. In some embodiments, the processing unit and the actuator control unit may comprise a single module. Thus, the words processor 14, 15 may be used to describe a combination of a processing unit and an actuator control unit.

The variable focus lens 11 is used in principle to support the adjustment of the patient's vision, rather than to correct the patient's vision. For example, in the case where the patient's vision is satisfactory and only accommodation is insufficient, there may be no need to correct the vision. The correction may also be supported by a conventional artificial lens 18, which is then typically implanted in the posterior chamber 19 of the patient's eye 20. The correction may also be supported by contact lenses or spectacles.

The variable focus lens 11 used in the ophthalmic assembly 10 according to the present invention may take different forms. In general, a variable focus lens can be considered to have variable optical power. Different embodiments of the variable focus lens have different features for causing a change in the optical power of the lens. The actuator may take one of several different forms, according to different embodiments. The actuator is configured to vary the diopter of the variable focus lens in accordance with a control value received from the processor. The processor is arranged to generate a control value based on a distance parameter received from the autofocus system, as will be described later.

According to a first embodiment, shown in fig. 3 to 5, the variable focus lens 11 is made of a deformable material and/or has a deformable shape and typically contains a fluid, such as a liquid. Such lenses are known as "deformable lenses". Typically, such variable focus lenses may comprise a membrane made of a resilient transparent material such as silicone, a flexible acrylic material, or any suitable impermeable elastomeric membrane. The actuator 12 of the ophthalmic component 10 comprises at least one compression element 21 arranged on the support 17 at the periphery of the lens. In some embodiments, the actuator comprises two compression elements 21 arranged on either side of the lens, which compression elements are movable relative to each other. When one compression element 21 is displaced with respect to the other or with respect to the lens, at least one of said compression elements acts on the deformable lens and changes its shape. Such shape changes are shown in fig. 3 to 5. In fig. 3, the lens 11 has two parallel faces. The parallel beams entering the patient's eye remain parallel as they exit the lens. In fig. 4, the lens 11 has a convex shape. The lens shown in fig. 5 has a concave shape. The diaphragm of the variable focus lens of this embodiment may be considered to be an element having a deformable shape, since its shape may change when acted upon by the compression element.

This change in lens shape has the effect of changing the focal length of the lens. Thus, controlling the displacement of the compression element 21 can control the focal length of the zoom lens 11.

According to an advantageous embodiment, the variable focus lens 11 comprises a rigid transparent fixed surface 22. The compression element 21 moves relative to the rigid surface 22 of the lens and thus causes deformation of the zoom lens 11.

According to another embodiment, one of the compression elements comprises a transparent piston in contact with one face of the lens 11. The piston can act on one face of the variable focus lens to deform it. According to one embodiment, the transparent piston is integral with one of the compression members.

In various embodiments of the above-described actuator 12, in which the actuator comprises two compression elements 21, the displacement of these compression elements is a relative displacement, i.e. one element moves relative to the other. More specifically, the distance between two elements may be increased or decreased. This means that one compression element may remain stationary while the other compression element moves, or both compression elements may move closer to or further away from each other while both compression elements move.

According to another variant, the actuator 12 comprises at least one electrode, for example an annular electrode, arranged on the support 17 at the periphery of the lens. The lens includes a membrane made of an electroactive polymer. By applying a voltage to the electrodes, the membrane is deformed, which has the effect of changing the focal length of the lens. The membrane is an element having a deformable shape.

Other types of lenses with variable focal length, in particular non-deformable lenses, may also be used.

In such a non-deformable variable focus lens, a variable focus lens containing two immiscible liquids may be proposed. One of these liquids is electrically conductive and the other liquid is electrically insulating. These liquids also have different refractive indices and are separated by an interface. The interface between two immiscible liquids forms a concave-convex surface whose shape is responsible for the optical path of the incident light. The shape of the relief surface can be changed in a controlled manner by applying a potential difference between the two liquids. The change in the shape of the concave and convex surface has the effect of changing the focal length of the zoom lens. In this embodiment, the concave-convex surface having a deformable shape can be considered as an element of the zoom lens.

Typically, such a lens having a concave-convex surface of deformable shape is formed within a rigid container. However, such a lens may be combined with the previous embodiments, i.e. with a deformable lens, so that the shape of at least a part of the container may also be deformed. For example, a flexible membrane on one side of the lens through which light from an object passes. Alternatively, both faces of the lens may have flexible membranes.

According to another variant, the variable focus lens may comprise a region containing liquid crystals. The refractive index of these liquid crystals varies according to an electric field applied to them. Controlling the electric field applied to the liquid crystal adjusts the refractive index and thus the focal length of the zoom lens.

According to a further variant, shown in figures 6 and 7, the lens 11 is a deformable lens and contains at least one liquid 23, the interior of the lens being connected to a reservoir 24 and a pump 25 acting as the actuator 12. The pump 25 may change the amount of liquid 23 contained in the lens, thereby deforming the lens 11. This has the effect of changing the focal length of the zoom lens. Also in this embodiment, the flexible membrane of the lens may be considered as an element having a deformable shape.

The actuator 12 is based on the type of zoom lens and parameters such as the shape of the lens, the material from which the lens is made, its contents, etc.

According to the embodiment shown in fig. 3 to 5, the actuator 12 comprises two annular compression elements 21 arranged on the support 17 on either side of the lens periphery. These compression elements are for example of the capacitive, electrostatic or piezoelectric type. In the absence of electrical excitation, the compressive elements are separated by a predetermined distance. According to an advantageous embodiment, the predetermined distance may be set separately. The predetermined distance corresponds to a focal length of the zoom lens, referred to as a default focal length.

In the example of a variable focus lens comprising two liquids that are immiscible, the actuator 12 is formed by a power supply capable of generating a potential difference in a controlled manner.

In the example of changing the shape of the variable focus lens by changing the amount of liquid contained in the deformable housing, the actuator 12 comprises a pump 25 and a reservoir 24.

It will be apparent that the actuator 12 and its mode of operation depend on the type of zoom lens used and the manner in which the focal length is varied and controlled.

The automatic focusing system 13 of the ophthalmic module 10 according to the present invention has the function of specifically determining the focal length of the variable focusing lens 11 for achieving the optimal vision of the user. Obviously, the focal length varies according to the distance of the object at which the user is looking. To achieve this goal, the autofocus system determines a distance parameter, the nature of which varies according to the implementation.

The autofocus system 13 is advantageously arranged in the vicinity of the zoom lens 11 on the support 17 in an area where the ophthalmic component receives sufficient light from the object at which the user is looking. For example, fig. 1 and 8 each show the autofocus system positioned close to their corresponding zoom lenses.

In the first embodiment, the autofocus system 13 includes an autofocus sensor 26 and an autofocus lens system 27. In this embodiment, the autofocus lens system comprises a single autofocus lens 27, wherein the distance between the autofocus sensor and the autofocus lens is variable. When the user looks at the object, the position of the autofocus lens, or more precisely the distance between the autofocus lens 27 and the autofocus sensor 26, is changed. An image of the object is formed on the autofocus sensor 26 and the contrast of the image is measured. The autofocus lens 27 is moved until the measured contrast is maximum. The distance between the autofocus lens 27 and the autofocus sensor 26 is then determined, which forms the distance parameter of the autofocus system.

By placing the autofocus system near the zoom lens, it is ensured that the autofocus lens system is placed near the zoom lens, such that the autofocus system processes substantially the same image as the image formed in the user's eye by the target object at the user's gaze. In the above embodiments, the autofocus lens may be described as a microlens, where its diameter is less than 1 millimeter (1mm) and may be as small as 10 micrometers (10 μm). This minimizes the distance between the autofocus lens and the zoom lens.

According to one embodiment, the position of the autofocus system may be selected to be anywhere around the circumference of the zoom lens, allowing different positions to be selected according to any particular constraints that need to be considered during placement of the component in the eye. For example, it may be desirable to have a particular orientation of the component once placed in the eye. Examples of specific orientations include an inferior orientation, a nasal orientation, or a temporal orientation, and selection of the orientation may be based on the visual field orientation and/or eyelid requirements. According to other embodiments, multiple autofocus systems may be provided on one assembly, such that one or the other autofocus lens system may be selected according to the benefit of its orientation.

In another embodiment shown in fig. 8, the autofocus system 13 includes an autofocus lens system having a plurality of lenses 28a, 28b, … …, 28n, each having a fixed focal length different from each other and disposed proximate to each other. Each lens generates an image on at least a portion of the autofocus sensor. Since the autofocus lens system is positioned adjacent to the zoom sensor, the multiple images formed by the multiple autofocus lenses are substantially the same image of the target object at which the user is looking. A separate autofocus sensor may be used for each separate lens or, conversely, a single autofocus sensor may be used for all lenses, with a different area or zone of the autofocus sensor dedicated to each lens.

According to various embodiments, the plurality of autofocus lenses of the autofocus lens system may be described as microlenses, wherein they may have a diameter of less than 1 millimeter (1mm) and may even be as small as 10 micrometers (10 μm) in diameter. This minimizes the distance between the autofocus lens and the zoom lens.

The plurality of microlenses may be considered to form a microlens array. Accordingly, embodiments of the present invention may include an autofocus system having an autofocus lens system including a microlens array and one or more autofocus sensors behind the microlens array to receive light from a target object passing through the microlens array. The autofocus lens system may be considered to be part of the rangefinder.

Accordingly, it can be considered that figure 8 illustrates an embodiment of an ophthalmic assembly having an autofocus system including an autofocus lens system having a microlens array. It can be considered to be used as a range finder. The microlenses each have a different fixed focal length, and each microlens within the array generates a corresponding image of a target object at which the user's line of sight is directed on the autofocus sensor. A separate autofocus sensor may be used for each separate microlens of the autofocus lens system. In addition, a single autofocus sensor may be used for all of the microlenses, with multiple different regions or areas of the autofocus sensor corresponding one-to-one to the multiple microlenses. The contrast of each image formed by the auto-focus microlens array can be measured. The focal length of the microlens that produces the image with the highest contrast can be used to provide a distance parameter for the autofocus system. Fig. 8 shows an example of how the microlens array is arranged close to and preferably in close proximity to the variable focus lens on the support of the ophthalmic component. Other arrangements are possible so long as it is followed that the microlens array is immediately adjacent to the zoom lens and each microlens in the array is immediately adjacent to each other. The number of microlenses in the array can also be selected according to design requirements.

There are two main types of microlenses, which are referred to as gradient index microlenses (GRINs) and micro fresnel lenses. They are discussed further below in this disclosure. GRIN microlenses may be coated with various coatings to provide a desired index of refraction. Thus, each lens in a particular microlens array may be coated differently. For example, a first lens in an array may have a coating of a first material, a second lens in the array may have a coating of a different material, and a third lens in the array may have a coating comprising layers of the first and second materials. Gradients of different refractive indices may also be formed across the microlens array using partial polymerization techniques (e.g., using ultraviolet light). In addition, the method of fabricating the micro fresnel lenses may be employed to fabricate a complete array of micro lenses each having a different refractive index.

Microlens arrays may also be printed. For example, drop on demand technology (DoD) may be used, which is similar to inkjet printing, in which a substrate is passed under a heated print head having nozzles for discharging droplets of fluid onto the substrate as the substrate passes under ambient pressure. The printhead has a piezoelectric transducer that can be controlled by providing appropriately formatted data to a printhead driver to provide the desired fluid drops onto the substrate. Thus, for fluids comprising suitable polymers, and where the substrate is part of an autofocus sensor of an ophthalmic assembly as described herein, a series of plano-convex polymer droplets forming a microlens can be deposited on top of the autofocus sensor. By selecting different polymers and by varying the printing parameters (e.g. data for the print head driver or the temperature of the print head or the size and/or shape of the nozzles of the print head), lenses with different fixed focal lengths can be made.

It is also possible to manufacture a microlens array in which each microlens is a microfluidic optical lens. Such a lens may be of a fixed focus type or a variable focus type. It has been mentioned that the autofocus lens system for embodiments of the invention may comprise a deformable lens.

These manufacturing techniques allow for the production of suitable microlens arrays for ophthalmic assemblies described herein having an autofocus system with an array of microlenses in which the appropriate miniature lenses can be placed very close together and adjacent to a zoom lens, wherein the refractive index of each microlens in the array can be suitably controlled to provide different refractive indices.

The contrast of each image formed by the autofocus lens 28 is measured. The focal length of the lens producing the image with the highest contrast forms the distance parameter of the autofocus system 13.

Alternatively, the focal distance that produces the maximum contrast can be inferred from measurements of the contrast of at least two adjacent images and preferably of at least three images.

Embodiments of the present invention in which the autofocus lens system includes a microlens array provide advantages related to reduced power consumption and thus extended battery life, as fewer moving parts need to be powered.

According to another embodiment, the autofocus system 13 includes at least one zoom autofocus lens. The focal length of the lens is varied and the contrast on the acquired image is determined. The focal length that produces the image with the highest contrast forms the distance parameter of the autofocus system.

According to some embodiments, the zoom-type lenses used within the auto-focus system may be of a deformable type, such as those described above for zoom-type lenses that are responsive to distance parameters provided by the auto-focus system.

The value of the distance parameter of the autofocus system 13 is sent to the signal processing unit 14. The signal processing unit 14 comprises a calculation module responsible for converting the distance parameter values of the autofocus system into focal length values of the zoom lens 11. The computing module may be calibrated globally or otherwise individually for each user.

Then, the focal length value determined by the calculation module of the signal processing unit 14 is sent to the actuator control unit 15 as a target value. The actuator control unit 15 then acts on the actuator 12 so that the zoom lens 11 adjusts its focal length in accordance with the assigned target value.

It is obvious that the way of performing the focal length adjustment depends on the type of the zoom lens 11 and the type of the actuator 12. Therefore, if the zoom lens 11 is deformable by a capacitive, electrostatic or piezoelectric type compression element 21, the control unit 15 of the actuator will act on the voltage applied to the compression element. If the variable focus lens 11 has a shape that can be changed by injecting or sucking in liquid, the control unit will act on the pump 25 to change the amount of liquid 23 contained in the variable focus lens.

The autofocus system 13 as well as the signal processing unit 14 and the actuator control unit 15 require at least one energy source or power supply 16. The power source may take different forms. It is also possible to provide not only one energy source but a plurality of different energy sources. The first energy source may be a battery, for example arranged at the periphery of the support 17. The second energy source may be a super capacitor or a rechargeable battery. The support 17 can also be provided with transparent or opaque photovoltaic cells. The user's body may also be used as an energy source. For example, the energy source may recover energy from body heat, muscle movements, fluid flow, and the like.

It should be noted that even if the energy originates, for example, from muscle movements, this is not comparable to prior art systems where deformation of the accommodative lens is produced by the ciliary muscle. Indeed, in the prior art, the deformation of the lens is directly related to the amplitude of the ciliary muscle displacement. If the amplitude is insufficient, the regulation will also be insufficient. In the ophthalmic assemblies described herein, the contraction of the muscles may be used to charge the battery. There is therefore no direct link between the amplitude of the movement of the muscles and the amplitude of the change in focal length of the zoom lens. Generally, the ophthalmic components described herein are implanted into the eye of a patient who is at least partially incapacitated. Therefore, the ciliary muscle is not generally used as an energy source.

A variety of energy sources may be combined, such as photovoltaic cells and rechargeable batteries.

The energy source is connected to the various components and/or units (auto focus system, signal processing unit … …) in order to provide them with the energy needed to perform their functions.

In case the power source 16 is rechargeable, for example in case of a battery or a super capacitor, a charging device is provided. According to an advantageous embodiment, the ophthalmic component 10 comprises an antenna 29 arranged at the periphery of the support 17. The antenna 29 may be used to charge the power supply 16 by electromagnetic induction.

The support 17 of the ophthalmic assembly 10 receives the different components described previously, namely the zoom lens 11, the actuator 12, the autofocus system 13, the signal processing unit 14, the actuator control unit 15, the power supply 16 and possibly the communication means. The support 17 also includes means 30 for holding the ophthalmic assembly 10 in place in the anterior chamber 31 of the patient's eye. The holding means 30 may have different shapes such as haptics (haptics). Two of these shapes are shown in fig. 1 and 9.

Since the ophthalmic component is placed in the anterior chamber 31 of a patient's eye and since the artificial lens 18 can be placed in the posterior chamber 19 of the same patient's eye, it is important that the shape of the support portion and the retention device 30 is compatible with the size and shape of the anterior chamber 31.

According to one aspect of the present invention, there is provided an ophthalmic component kit comprising two ophthalmic components as described above, one for each eye of a user. In an embodiment of such a kit of ophthalmic components, each ophthalmic component comprises communication means for communicating between the two ophthalmic components when they are implanted in separate eyes of a user, respectively. This provides a bi-directional operation where the function of one zoom lens depends on the operation of the other zoom lens and vice versa, which may for example help to provide autofocus with higher reliability, where the communication between the two components allows them to each confirm which object the user is most likely looking at.

The method of adjusting the vision of a patient operates as follows. First, the autofocus system 13 determines a distance parameter related to the object at which the patient's eye is looking. The distance parameter depends on the type of autofocus system used and the implementation chosen for the ophthalmic component 10. The distance parameter may be the actual distance between the patient and the object. The parameter may also be a distance range between the patient and the object. For example, the distance range may be defined, for example, as "near viewing distance" for viewing distances less than 50cm, "mid viewing distance" for viewing distances between 50cm and 1.50m, and "far viewing distance" for viewing distances beyond 1.50 m. In this case, the distance parameter is only one of the determined ranges. It is clear that more than three ranges may be defined and that the distance values of these ranges may differ from the given example.

In the case where the autofocus lens 27 is movable, the distance parameter may be the distance between the autofocus lens 27 and the corresponding autofocus sensor 26 at which the contrast of the image of the object at which the patient is looking formed by the autofocus lens is greatest.

When the autofocus lens 27 is a zoom lens, the distance parameter is the focal length of the autofocus lens at which the contrast of the image of the object focused on by the patient formed by the autofocus lens is the greatest.

In general, the distance parameter is a value determined by the autofocus system 13 and the signal processing unit 14, which may define the size that the focal length of the variable focus lens 11 should have in case the image of the object at the gaze of the patient formed by the lens with variable focal length becomes clear.

Several images are captured while changing the focal length of the autofocus lens 27, and then sent to the signal processing unit 14. The signal processing unit 14 determines which image has the greatest contrast and which focal length of the autofocus lens 27 the image corresponds to. Then, the signal processing unit converts the focal length value of the autofocus lens 27 into the focal length value of the zoom lens 11. The focal length value of the zoom lens is sent as a target value to the control unit 15 of the actuator. Then, the actuator 12 acts so that the focal length of the zoom lens 11 reaches the target value. Obviously, the manner in which the actuator 12 is controlled depends on the implementation chosen.

The object at which the patient is looking or in other words the object used for determining the distance parameter may be a region of the user's field of view. According to a preferred embodiment, this region is located around the center of the user's field of view and its extent is small enough that the distance between the different possible views of the scene at which the user is looking is not too large.

As described above, the ophthalmic assembly 10 is placed in the anterior chamber 31 of the patient's eye 20. The ophthalmic assembly 10 can be implanted in an eye that has had the lens replaced with an artificial lens or an eye with a natural lens.

In the first embodiment, the ophthalmic assembly 10 is implanted without regard to the patient's actual vision. The ophthalmic component functions to allow the patient to adjust vision. In this embodiment, the default focal length of the ophthalmic component cannot be changed once the ophthalmic component has been placed in the patient's eye.

According to another variation, the default focal length may be changed after the ophthalmic component is implanted in the eye of the patient. This may be done, for example, by injecting or removing fluid from the variable focus lens. This variant enables the default focal length of the variable focus lens to be adjusted taking into account the actual vision of the patient. The default focal length typically corresponds to the patient's distance vision. Which corresponds to the focal length of the zoom lens without actuation of the actuator 12. Thus, the lens 11 with variable focal length assumes a configuration that gives the user good distance vision if the actuator is no longer powered.

In at least some embodiments, the default focal length can be preset prior to implantation of the ophthalmic assembly 10 into the eye of a patient and can be changed or adjusted after implantation. The default focal length may be preset by the same mechanism used to change the focal length during use of the ophthalmic assembly. In another embodiment, the presetting may be by a first mechanism, while the focal length for immediate adjustment is changed by another mechanism. An example of a possible implementation is to use a lens containing a liquid 23 and a pump 25 for presetting a default focal length and an actuator 12 comprising a compression element 21 in the form of two ring electrodes to perform the adjustment function.

In typical embodiments, the focal length of the variable focus lens varies in the range of-1 to +4 diopters, and preferably in the range of-0.5 to +3.5 diopters or 0 to +3 diopters.

In a preferred embodiment, the ophthalmic component comprises communication means 32 for receiving information and/or commands from the outside and optionally for transmitting data to the outside. The communication means 32 comprise in particular an antenna 33. In the case of charging the battery by induction, the antenna 33 of the communication device 32 may be the same as the antenna 29 for the power supply 16, or may be a separate antenna or a separate inductive loop.

After placing the ophthalmic assembly 10 in the eye of a patient, the ophthalmologist can determine the size that the default focal length of the variable focus lens 11 should have. This default focal length may then be set, for example, by a dedicated application. The setting instruction of the default focal length may be received by the antenna 33 of the communication device 32 and processed by the signal processing unit 14. The signal processing unit may then act on the actuator control unit 15 to set the default focal length.

The default focal length may be set immediately after the ophthalmic assembly 10 is implanted in the eye of the patient. For example, it is also possible to adjust the patient after a few months or years as his vision changes.

By way of further example, the user may also have an application that allows him to activate or deactivate the autofocus system 13. In the case where the user performs a constant focus task that does not require viewing distance, such as reading or working in front of a computer screen, the user may choose to disable the autofocus system. This deactivation may be accomplished by transmitting a signal that is received by the antenna 33 of the communication device 32 and processed by the signal processing unit 14. The actuator control unit 15 may then set the focal length of the variable focus lens 11 to a defined value (which may for example correspond to the focal length of the lens just before deactivation), a value selected by the user or a range of vision or a default focal length value. The user may then re-enable the autofocus system 13 by sending a corresponding signal to the ophthalmic component 10. According to one embodiment, the autofocus system 13 may be deactivated by inhibiting the powering of the actuator 12. Depending on the implementation, this may cause the zoom lens 11 to remain in the state it reached just before deactivation. In another implementation, this may also cause the zoom lens to assume a default focal length value.

The antenna 33 of the communication device 32 may also be used to transmit signals to the outside. This may be done especially when the power supply 16 needs to be charged. In this case, the alarm signal may be transmitted via the antenna 33 to a suitable reading device or interaction device, for example a smartphone. Such a reading device or interaction device can also be used for interrogating the ophthalmic component and for example for learning about the available energy, receiving an estimate of the battery life, etc.

Ophthalmic assemblies according to the present invention may be implanted in a patient without regard to vision correction. For example, it may restore the accommodative function of vision to a user who has lost accommodation but retains the natural eye lens. In this case, the ophthalmic component may be used, for example, by the spectacle wearer as a replacement for progressive spectacles. In this case, the basic correction of vision is provided by a pair of non-progressive spectacles. The accommodation function is provided by the ophthalmic component. This can be particularly beneficial for people who cannot tolerate progressive glasses. This may also be particularly beneficial for persons wearing contact lenses.

Ophthalmic assemblies according to the present invention may also correct the patient's vision to some extent after lens replacement surgery. Post-operative refractive errors, for example in the case of artificial lenses, can be due to the difficulty of performing very accurate biological measurements and in any case to variations in the patient's vision.

Since the ophthalmic component is primarily concerned with accommodation and not correction, the magnitude of lens motion is very small. This means that the size of the subject component can be kept small and the required power can be low. This also helps to reduce the size of the ophthalmic component.

This reduction in size enables the placement of the ophthalmic component in the anterior chamber of the eye, thus leaving room for an artificial lens in the posterior chamber of the eye.

Embodiments of the present invention may employ microlens fabrication techniques as described below to produce any of the autofocus lens systems described herein. A typical microlens may have a planar surface and a convex surface to refract light. The convex surface may be spherical or aspherical, depending on the type of microlens. Various layers of optical material may also be used to achieve the desired refractive properties of the microlenses.

Two known types of microlenses are gradient index microlenses (GRINs) and micro fresnel lenses. Some GRIN microlenses have two flat parallel surfaces for passing light, and can achieve focusing due to the variation in refractive index across multiple lenses. In other GRIN microlenses, one or the other or both surfaces of the lens may have a convex or concave shape, thereby achieving focusing power by virtue of the shape of one or more surfaces of the lens. In other GRIN microlenses, the focusing effect can be achieved either by a change in refractive index across multiple lenses or by the shape of one or more surfaces of a lens.

The micro fresnel lens can be very thin overall and therefore very lightweight. This type of lens has a set of concentric curved surfaces that contribute to the focusing action of the light. They have grooves with stepped edges or multiple levels that can be considered to approximate the shape of an ideal lens. They have the advantage that their manufacture and replication can be carried out using standard semiconductor processing techniques.

Several different techniques are known for fabricating GRIN microlenses. They include neutron radiation irradiation, chemical vapor deposition, partial polymerization, ion exchange, ion packing, and laser direct writing. All of these techniques are well known and each technique may have its own effect on the resulting microlens. For example, in ion exchange, glass is immersed in a liquid melt along with lithium ions. As a result of diffusion, sodium ions in the glass are partially exchanged with lithium ions, with a large amount of exchange occurring at the edges.

The micro fresnel lenses can be fabricated using standard microfabrication processes including masks or molds, photoresists and selective uv exposure. For example, a uv-curable polymer may be deposited on a glass substrate. A mold having the desired pattern of micro fresnel lenses (e.g., a series of concentric grooves with beveled edges) is applied using pressure to a substrate having a uv-curable polymer. This pressure causes the excess polymer not protected by the mold to be expelled. The remaining polymer is exposed to a source of ultraviolet light below the glass, thereby curing the polymer remaining in the mold. When the mold is removed, the cured polymer profile remains with the desired shape of the concentric grooves with the beveled edges defined by the mold, thereby providing a micro fresnel lens.

According to embodiments in which the autofocus system includes an autofocus lens system having a deformable lens, an actively deformable microfluidic optical lens array may be used to fabricate such a lens. A fluidic optical lens is a fluid-containing lens, such as the aforementioned liquid-containing lens. The fluidic optical lens exhibits the characteristics of a microlens as described above. When placed in an array, they are used in embodiments of the autofocus lens system of the invention. The microlens array may be formed by injecting a liquid into the lens array, with each adjacent lens connected such that the fluid can flow through all of the lenses. A fixed focal length microlens array can be achieved if the injection is provided by the microlens array only during system manufacture and not during its deployment. The curvature of the microfluidic optical lens membrane is fixed, but the focal length can also be adjusted by refilling or draining the liquid inside the system on a lens-by-lens basis after the injection step, thereby providing a suitable array of lenses with different fixed focal lengths for use in the autofocus lens system of embodiments of the present invention.