CN115542576A

CN115542576A - Dynamic retinal defocus control method and system and ophthalmologic device

Info

Publication number: CN115542576A
Application number: CN202211143884.7A
Authority: CN
Inventors: 陈昕阳; 余威德; 王晓瑛; 薛枫
Original assignee: Individual
Current assignee: Individual
Priority date: 2022-09-20
Filing date: 2022-09-20
Publication date: 2022-12-30

Abstract

The invention relates to a dynamic retinal defocus control method, a dynamic retinal defocus control system and an ophthalmologic device, wherein the control system comprises: the dynamic out-of-focus lens is used by a user, and the degrees of different areas on the dynamic out-of-focus lens are adjustable; the sensing module is used for sensing the far and near focal length change of an eyeball visual object; the two control units are used for matching with physiological regulation of the eyeballs of the user during distance switching and dynamically adjusting the degrees of different areas on the dynamic focusing lens in different modes so as to maintain the form that the myopic defocusing amount at the periphery of the retinas of the eyeballs of the user is larger than the myopic defocusing amount at the center; and the trigger unit judges the near-looking and far-looking state according to the sensing information of the sensing module and respectively triggers the two control units to work. The invention solves the problems that the traditional defocusing lens can not effectively correct the central or peripheral defocusing of the retina generated in the physiological regulation dynamic change of the eyeball, and the like, and can further optimally slow down the lengthening of the axis of the eye and the deepening of myopia.

Description

Dynamic retinal defocus control method and system and ophthalmologic device

Technical Field

The invention relates to the technical field of myopia correction, in particular to a dynamic retinal defocus control method, a dynamic retinal defocus control system and an ophthalmic device.

Background

Myopia is a very wide range of diseases worldwide, with Axial myopia (Axial-length-related myopia) occurring during childhood development as the main type of myopia, occurring mainly due to the increase in the Axial transition of the eye during the development of the eyeball (Axial elasticity). Currently, methods for preventing and controlling axial myopia include orthokeratology (Ortho-K lenses), defocus Soft contact lenses (Defocus Soft contact lenses), defocus frame lenses (Defocus space lenses), low-intensity red-light (RLRL) therapy, and Low-concentration atropine eye drops.

The design principle of the defocusing lens product is different from that of the traditional myopic single-focus lens, the single-focus lens is integrally of the same diopter, but the human retina is of an arc shape, and the radian of the periphery of the retina is larger. That is, after the dioptric imaging of the conventional myopia lens, although the object image in the central area of the retina can be exactly focused on the macular region in the visual center to make the object clearly seen, the object image in the periphery of the retina is focused on the rear side of the retina to form peripheral hyperopic defocus (peripheral hyperopic defocus) of the retina, which stimulates the retina to prolong and accelerate the axial development of the eye, resulting in the increase of the myopia degree. The principle of the defocusing lens is that the myopic degree is corrected through a special optical design, so that an object image falls on the central retina, the hyperopic defocusing of the periphery of the retina is corrected, and the peripheral image is focused on the retina or the front side. For example, patent CN101317120B discloses an out-of-focus lens, namely a commercially available kale zeiss like growing music (MyoVision) lens, which makes a +1.00D diopter change design from the near central area to the periphery of the lens by designing out-of-focus zones with different ranges from the center to the periphery, so that a near-sighted annular out-of-focus zone can be generated at the periphery of the retina; for example, patent CN104678572B discloses another out-of-focus lens, i.e. the lens of nyosmic (Miyosmart) of the japanese Hoya company, which can make the center of retina and its peripheral area have the mutually interlaced myopic out-of-focus state of +0D focal length falling on the central retina and + 2.00D- +3.50D diopter focusing on the front side of retina, forming regional emmetropia and myopic out-of-focus by designing special optical structure through the paracenter area and peripheral area; there are numerous other multi-zone coaxial corneal contact designs available on the market for myopia prevention and control. The optical stimulation of the focusing lens can send out a signal for slowing down the lengthening of the axis of the eye to the eyeball, thereby slowing down the development of myopia deepening.

However, the current defocus lens design has many limitations, because the human eyeball lens is in a constantly and dynamically changing Accommodation (Accommodation) state during the daily looking at near and far, and there are cases that the Accommodation stimulus and the Accommodation response are not necessarily equal, that is, the Accommodation induced by different object image focal lengths has different Accommodation response speeds during the Accommodation movement, so the retina is actually in various constantly changing far and near defocus stimulus states, and further, because the lens itself is not an ideal aspheric lens optical refraction form and is changed, and in addition, the retina surface has a change of radian, which finally results in that each area of the retina surface is subjected to uneven defocus stimulus. The existing myopia prevention and control defocusing lens belongs to a defocusing lens in a static fixed optical state, and the optometry fitting mode is to fit a correction diopter which is used as a base line in a manner of looking at a standard fixed center right in front and in a 5-meter distance state, so that the central or peripheral defocusing change of a retina generated in the physiological regulation dynamic change of an eyeball cannot be effectively dealt with in the design. Although patent CN107219641B discloses a pulse type myopic retinal defocus technique, which uses periodic, continuous pulse type retinal myopic defocus that human eyes cannot perceive to stimulate eyeballs, this technique is also similar to the above-mentioned numerous static myopic defocus schemes, and does not solve the problem of unstable central-peripheral retinal defocus state caused by the physiological accommodation movement state of crystalline lens that human eyes are actually looking away, looking near rapidly or switching smoothly at any moment in most cases, and further fails to solve the problem of unstable defocus amount caused by the long-term and near processes when the eye accommodation fatigue is abnormal, and how to stimulate retinal defocus state in the dynamic state.

Disclosure of Invention

In order to solve the problems, the invention provides a dynamic retinal defocus control method, a dynamic retinal defocus control system and an ophthalmic device, which solve the problems that the traditional defocusing lens cannot effectively correct central or peripheral retinal defocus generated in the physiological regulation dynamic change of eyeballs, and the like.

The invention is realized by the following scheme: a dynamic retinal defocus control system, comprising:

the dynamic out-of-focus lens is used by a user, and the degrees of different areas on the dynamic out-of-focus lens are adjustable;

the sensing module is used for sensing the far and near focal length change of an eyeball visual object;

a control module, the control module comprising:

the first control unit is used for maintaining the form that the myopic defocus amount at the periphery of the retina of the eyeball of the user is larger than the myopic defocus amount at the center in a mode that the dynamic defocus lens is controlled to increase the positive sphere power from the optical peripheral area to the optical central area by negative acceleration during working, and the first control unit is in control connection with the dynamic defocus lens;

a second control unit for maintaining the form that the myopic defocus amount at the periphery of the retina of the eyeball of the user is larger than the myopic defocus amount at the center in a mode of controlling the dynamic defocus lens to decrease the spherical power from the optical peripheral area to the optical central area at positive acceleration during working, wherein the second control unit is in control connection with the dynamic defocus lens;

the triggering unit is used for acquiring the sensing information of the sensing module and judging whether the eyeball of the user is a triggering unit which triggers the first control unit to work when the eyeball is seen from far to near or triggers the second control unit to work when the eyeball is seen from near to far according to the sensing information, and the triggering unit is connected with the sensing module, the first control unit and the second control unit.

The invention dynamically controls the degrees of different areas of the dynamic out-of-focus lens based on the dynamic out-of-focus lens, and provides dynamic near-out-of-focus stimulation to the center and the periphery of the retina by matching with the characteristic of dynamic physiological regulation of the eyeball so as to maintain the form that the near-out-of-focus amount at the periphery of the retina of the eyeball is larger than that at the center, thereby solving the problem that the traditional focusing lens cannot effectively correct the far-out-of-focus phenomenon of the center or the periphery of the retina in the far-near regulation caused by dynamic change of the physiological regulation of the eyeball, further reducing the lengthening of the axis of the eye to the maximum extent and slowing down the deepening of the myopia.

The dynamic retina defocusing control system is further improved in that the first control unit ensures that the increment of the myopic defocusing amount in the center of the retina is not more than +0.50D when controlling the dynamic defocusing lens to increase the spherical power, and the second control unit ensures that the increment of the myopic defocusing amount in the center of the retina is not more than +0.25D when controlling the dynamic defocusing lens to decrease the spherical power.

In a further improvement of the dynamic retinal defocus control system of the present invention, the first control unit and the second control unit are set such that the absolute value of the negative acceleration is larger than the absolute value of the positive acceleration at equal distances.

The dynamic retinal defocus control system of the invention is further improved by further comprising a tracking module for tracking the visual center position of the eyeball of the user, wherein the tracking module is connected with the control module, and the control module comprises a positioning unit for positioning the optical center axis of the dynamic defocus lens according to the visual center position and maintaining the optical center axis at the visual center position.

The dynamic retinal defocus control system is further improved in that the dynamic retinal defocus lens comprises a plurality of micro lenses which are densely and regularly arranged, and each micro lens can be independently activated by the control module and adjusted in power.

The dynamic retina defocus control system is further improved in that the dynamic defocus lens is a bionic flexible lens with an eyeball lens-imitating structure, and the control module is arranged to adjust the degrees of different areas of the dynamic defocus lens in a mode of enabling the bionic flexible lens to deform through dynamic stretching.

The dynamic retinal defocus control system is further improved in that the dynamic defocus lenses are divided into two groups and are respectively used for the left eye and the right eye of a user, and the first control unit and the second control unit are respectively connected with the two groups of dynamic defocus lenses and can select one or control the two groups of dynamic defocus lenses simultaneously.

The invention also provides an ophthalmic device for dynamic retinal defocus control, which comprises the dynamic retinal defocus control system.

The invention also provides a dynamic retinal defocus control method, which comprises the following steps:

arranging dynamic out-of-focus lenses with adjustable degrees in different areas at the eyeballs of a user;

sensing the far and near focal length change of an eyeball sight object of a user by using a sensing module;

acquiring sensing information of the sensing module by using a trigger unit and judging the sight line state of eyeballs of the user according to the sensing information:

when the user looks from far to near, a first control unit is triggered to work, the first control unit controls the dynamic out-of-focus lens to increase the positive spherical power from the optical peripheral area to the optical central area by negative acceleration, and the form that the near-sighted out-of-focus amount at the periphery of the retina of the eyeball of the user is larger than the near-sighted out-of-focus amount at the center is maintained;

and when the user judges that the user looks from near to far, the second control unit is triggered to work, the second control unit controls the dynamic defocusing lens to decrease the spherical positive power from the optical peripheral area to the optical central area at a positive acceleration, and the form that the myopic defocusing amount at the periphery of the retina of the eyeball of the user is larger than the myopic defocusing amount at the center is maintained.

The dynamic retinal defocus control method is further improved in that the visual center position of the eyeballs of the user is tracked by the tracking module while the sensing module is used for sensing;

the positioning unit positions the optical center axis of the dynamic through-focus lens according to the visual center position and maintains the optical center axis at the visual center position before the first control unit and the second control unit are triggered and start to operate.

Drawings

Fig. 1 shows a diagram of the physiological regulation of the eyeball in a general case.

FIG. 2 shows a schematic diagram of the retinal defocus pattern of the eye accommodation when-2.50D myopia is not worn.

FIG. 3 shows a schematic diagram of the retinal defocus pattern of the eye adjusted for-2.50D myopia with normal single vision glasses.

Fig. 4 shows a schematic diagram of the contrast of the in-eyeball out-of-focus plane morphology when-2.50D myopic glasses are not worn and common out-of-focus glasses are worn.

FIG. 5 shows a schematic diagram of the comparison of the intra-ocular focal plane morphology between the non-dynamic defocus control when accommodation delay occurs from far to near myopia at-2.50D and the dynamic retinal defocus control of the present invention.

Fig. 6 shows a schematic diagram of the present invention for maintaining the optical central axis at the visual central position by dynamic retinal defocus control.

Fig. 7 is a diagram showing the form of retinal defocus control during distance and near vision under dynamic retinal defocus control of the present invention.

Fig. 8 is a graph showing a defocus amount variation at different positions on the retina during a hyperopic process under the dynamic retinal defocus control of the present invention.

Fig. 9 is a graph showing a comparison of the change rate curves of the peripheral-central defocus amount difference values of the retina in a state of control using the first control unit and the second control unit, respectively, when the distance is the same.

FIG. 10 shows a focal plane topography of the dioptric profile of the dynamic out-of-focus optic and the corresponding near-accommodative reflection of the lens of the eye under dynamic retinal defocus control.

FIG. 11 is a schematic plan view of a dynamic defocused lens of a voltage controlled array liquid crystal microlens cell assembly.

Figure 12 shows a schematic of the power and corresponding focal plane shape of the near-accommodating reflex of the lens of the eye using a voltage controlled array of liquid crystal micro-lens cells.

Figure 13 shows a schematic diagram of the focal plane morphology of the bionic flexible lens dynamic stretching changing dynamic out-of-focus lens and the corresponding near-accommodation reflex of the eyeball lens.

Fig. 14 shows a diagram of the complementation of binocular fusion in a state where the two eyes asymmetrically control the dynamic out-of-focus lens when the two eyes are simultaneously watching the same distance and the same object.

Fig. 15 is a schematic diagram showing an embodiment of the dynamic retinal defocus control trainer for monocular adjustment training in the invention.

Detailed Description

Referring to fig. 1 to 4, in daily life, the eyeball has various actions of gazing at far and near positions to track an object, the focal distance projected into the eyeball is constantly changed at far and near positions, and the crystalline lens 2 and ciliary muscle in the eyeball are in a constantly changing movement state to adapt to the change of the focal distance at far and near positions, so as to enable the object image to be clearly imaged at the macular region M in the center of vision all the time. Further, in order to clearly see the object whose image is switched between near and far, the brain can make the crystalline lens 2 in the eyeball physiologically adjust, when the ciliary muscle is relaxed (as shown in the time T0 of fig. 1), the surface curvature of the crystalline lens 2 changes smoothly and the thickness of the crystalline lens becomes thin, the refractive power of the crystalline lens is reduced, the light emitted by the object at a distance is just converged on the retina 1, and the eyeball can see the object at a distance; when the ciliary body contracts (e.g., at time T2 of fig. 1), the lens 2 becomes thicker and has an increased surface curvature, the refractive power for light becomes greater, light from nearby objects is focused on the retina 1, and the eye can see nearby objects clearly.

When the object is viewed from far to near, the eye will produce accommodation reaction, which can make the radian of front and back surfaces of crystalline lens become convex, and enhance the refractive power of eye, further make the object image focus on retina clearly. Further describing, the neural conduction process of lens accommodation: the human eye sees a blurred visual image → lateral geniculate → optic zone cortex → cortical brainstem bundle and mesencephalon bundle → mesencephalon median nucleus → mydriatic nerve miosis nucleus → parasympathetic anterior fibers → transkinetic optic nerve, ciliary ganglion → Ciliary nerve → annular muscle contraction of Ciliary body (Ciliary muscle) → zonules (Suspensory ligands) relax → the convex and concave lens thickness increases, at which time the refractive power increases, allowing the focus of the object image to focus on the fovea of the macula of the retina.

On the one hand, however, when the ciliary muscle of lens 2 is performing a tight, relaxing movement of accommodation, either far to near or near to far, there are situations where the accommodation stimulus and accommodation response are not necessarily equal, such as: the regulation response is less than the regulation stimulus, and is the regulation lag; the response to regulation is greater than the stimulation to regulation, leading to regulation. Accommodative lag is common in humans, where the lag is approximately +0.50D to +0.75D diopters, where central and peripheral hyperopic defocus occurs. On the other hand, in the process of stimulating the crystal to adjust movement with different distance and near focal lengths, a phenomenon called accommodation micro movements (AMFs) occurs, which indicates that the human eye adjusts for each distance, and in addition to different adjustment speeds and adjustment amounts, extra minute high-frequency flutter movement exists, so that unstable distance or near vision defocus is formed on the retina at any time.

Further, in the case of a person wearing an eye for a long time, the ciliary muscle of the eye may be in a state of movement contraction fatigue, which causes a slow accommodation reaction due to fatigue during the switching process from far to near, fig. 1 shows a schematic view of the physiological accommodation state of the eyeball in a general case, the time T0 is the far viewing state, the time T0' is just switched to the near viewing state, the accommodation movement of the lens 2 cannot follow the amount of the accommodation stimulus, and there is an accommodation delay time of T2-T0', during which the accommodation delay time, such as time T0' and time T1, central hyperopic amounts Df1 and Df2 of the retina (Df 1> Df2, which gradually decreases with the progress of accommodation) are generated, the focal length of the objective image can be focused at the central macula M of the retina only after the lens 2 adjusts, i.e., at the time T2, and during this accommodation process, the retina is stimulated by the amounts Df1 and Df2, the areas corresponding to A1 and A2 are gradually increased, and the areas corresponding to A1 and A2, which gradually increase the myopia and a high frequency of the accommodation process can be easily induced by the myopia and the myopic axis.

And for the case of myopia without glasses, referring to fig. 2, fig. 2 shows a schematic diagram of the retina defocus form adjusted by the eyeball when-2.50D myopia without glasses is taken. The time T0 is a far-looking state, at this time, a focal plane B formed by the actual focal length of the object image falls on the front side of the retina 1, so that the visual object is blurred, and the peripheral retina is continuously stimulated by far-looking defocus; when T1 is in a near state and the crystalline lens 2 is not adjusted, the adjustment is delayed due to the adjustment fatigue of the crystalline lens 2, more hyperopic defocus Df is generated in the process of using eyes, and the hyperopic defocus stimulus area A of the retina 1 is larger; the time T2 is when the lens 2 is adjusted, at this time, the peripheral retina still has hypermetropia defocusing, so that the eyeball is subjected to the risk of the increase of the myopia axis, and the myopia is easily deepened. With further reference to fig. 3, fig. 3 shows a schematic view of the eye's accommodation of retinal defocus when wearing ordinary single-vision glasses in-2.50D near vision. Further, when the ordinary single-vision spectacles 3 are worn, although the optical focus falls on the central region of the retina at the time of looking far, the vision is clearly corrected, more hyperopic defocus is generated in the periphery of the retina, and during the switching from far to near, the amount Df '> Df increases, whereas the hyperopic defocus stimulus area a' > a increases, and the myopia is more easily deepened, and in the case of abnormal accommodative fatigue, continuous overcorrection at the time of looking near may be caused, and a large amount of persistent hyperopic defocus is generated.

Referring to fig. 4, fig. 4 is a schematic diagram showing a comparison of the forms of the defocused planes in the eyeball when-2.50D myopic glasses are not worn and common defocused glasses are worn. When the glasses are not worn, the focal plane B (namely the plane on which the focus of the object image is formed) is in a form that the periphery of the retina presents hyperopic defocusing, the central light beam is focused on the front side of the retina, so that the visual objects are blurred, and the retina is stimulated to cause the axis of the eye to grow. When the ordinary afocal lens 4 is worn, the form of the focal plane B' is changed, the focal distance of the central area of the retina vision is corrected, the hyperopic defocusing of the periphery of the retina is eliminated, the myopic defocusing amount of the periphery of the retina is increased, the hyperopic defocusing stimulation of the periphery is eliminated while the clear object image in the central area is not influenced, and the deepening of myopia is delayed. To date, the out-of-focus lens has obtained effective myopia prevention and control effect verification clinically, and gradually becomes the mainstream trend of myopia prevention and control products.

There are many limitations to the current design of off-focus lenses. As mentioned above, the eyeball of human is in a constantly dynamic adjusting state, and there are situations that the adjusting stimulus and the adjusting response are not necessarily equal, and in the adjusting process, the adjustment of different focal lengths has different adjusting response speeds, so that the retina is actually in various constantly changing far and near vision defocusing stimuli. Further referring to fig. 5, although the normal defocus spectacles 4 are worn to form a focal plane of near-sighted defocus in the periphery of the retina, the conventional fitting method of the off-focus lenses is a fixed focal plane and a correction diopter which is fitted at a fixed distance of 5 meters from the standard center right in front, and the phenomenon of defocus in the center or periphery of the retina which is generated in the dynamic change of the physiological adjustment of the eyeball cannot be effectively corrected in the design, as shown in fig. 5, after the normal defocus spectacles 4 are worn, the stimulation Df of far-sighted defocus in the center of the retina and the area a of the stimulation may occur in the adjustment process of far-near switching, and the control effect of the increase of the eye axis is affected.

Based on the above problems of the conventional zoom lens, there are some designs of zoom lenses, such as a design for controlling the Liquid Crystal (LC) alignment direction by using voltage variation to zoom the lens, specifically, a liquid crystal zoom lens for deep optics for correcting presbyopia or a multi-layer liquid crystal lens zoom apparatus disclosed in patent CN113196141A, which can improve the zoom response time and zoom amount of the lens. However, the zoom designs do not provide a specific dynamic control method which can be matched with the dynamic physiological regulation of the eyeball, and further do not provide the concepts of retina dynamic defocus control based on ophthalmic treatment, myopia defocus amount increase around the retina, retina retardation of myopia, axial development retardation of the myopia, and the like. The invention provides a dynamic retinal defocus control method, a dynamic retinal defocus control system and an ophthalmological device, which are matched with eyeball dynamic physiological regulation to provide dynamic myopic defocus stimulation to the center and the periphery of a retina so as to maintain the form that the myopic defocus amount at the periphery of the retina of an eyeball is larger than the myopic defocus amount at the center. The following describes the dynamic retinal defocus control method, system and ophthalmic device with specific embodiments in conjunction with the accompanying drawings.

Referring to fig. 5, a dynamic retinal defocus control system includes:

the dynamic out-of-focus lens 5 is used by a user, and the degrees of different areas on the dynamic out-of-focus lens 5 are adjustable;

a sensing module 6 (shown in fig. 6) for sensing the distance and focus changes of the eyeball optic;

a control module, the control module comprising:

a first control unit for maintaining the form that the near defocus amount at the periphery of the retina of the eyeball of the user is larger than the near defocus amount at the center in a mode of controlling the dynamic defocus lens 5 to increase the positive sphere power from the optical peripheral area to the optical central area by negative acceleration during working, wherein the first control unit is in control connection with the dynamic defocus lens 5;

a second control unit for maintaining the form that the near-sighted defocus amount at the periphery of the retina of the eyeball of the user is larger than the near-sighted defocus amount at the center in a mode that the dynamic out-of-focus lens 5 is controlled to decrease the spherical power from the optical peripheral area to the optical central area by positive acceleration when the optical lens works, wherein the second control unit is in control connection with the dynamic out-of-focus lens 5;

Specifically, the dynamic through-focus lens 5 may include a plurality of microlenses arranged in a dense regular pattern, and each of the microlenses can be individually activated and adjusted in power by the control module. As shown in fig. 11 and 12, a plurality of liquid crystal micro lens units 51 are arranged in a row on the dynamic defocus lens 5, the control module is electrically connected to each liquid crystal micro lens unit 51, the diopter of the corresponding liquid crystal micro lens unit 51 is controlled to be increased or decreased by adjusting the voltage, and the defocus variation range are controlled to present the stimulation form of the required focal plane B. The dynamic defocusing lens 5 can also be a bionic flexible lens with an eyeball lens-like structure, as shown in fig. 13, the control module is configured to adjust the degrees of different areas of the dynamic defocusing lens in a manner that the bionic flexible lens is deformed by dynamic stretching. Of course, the dynamic through-focus lens 5 is not limited to the above configuration.

In addition, referring to fig. 7 and 8, regarding the control of the dynamic defocus lens at the time of distance switching, fig. 7 shows a schematic diagram of the control form of the retinal defocus plane during the distance and near vision under the dynamic retinal defocus control of the present invention, and fig. 8 shows a graph of defocus variation at different positions on the retina during the distance and near vision under the dynamic retinal defocus control of the present invention. Such as defining a retinal defocus area includes: a P0 region (i.e., a central region) ranging from 5 to 10 degrees; the P1 area (namely the first section of peripheral defocusing ring) ranges from 10 degrees to 20 degrees; the P2 region (i.e. the second segment peripheral defocused ring) has the following range: 20 to 30 degrees. The left side picture is the distance of looking far 3 meters, and when the object that looks far away is adjusted to the cooperation lens, the control to the myopic defocus of three regions is: p0= +0.25d, p1= +2.00d, p2= +4.00D; the right graph shows that the distance of looking near 0.4 m, when the lens is matched to adjust and increase to see a clear object, the control of the myopic defocus amount of the three areas is as follows: p0= +0.50d, P1= +3.00d, P2= +6.00D. In the above example, the difference in the change in the amount of defocus of the spherical positive power toward the periphery of the retina increases as the distance is seen. Further, in looking at a distance of 3 meters far to a distance of 0.4 meters near, referring further to fig. 5, still further, the eyeball has the characteristic of physiological accommodation delay, the previous power setting on the lens causes the center and periphery of the retina to produce a hyperopic defocus amount Df, and in order to reduce the area of the area a where the retina is stimulated by the hyperopic defocus amount Df, the first control unit is used to control the myopic defocus amount increment of the P0 area to be +0.25D, the myopic defocus amount increment of the P1 area to be +1.00D, and the myopic defocus amount increment of the P2 area to be +2.00D, so that the focal plane B is changed from a "pan-and-pan" configuration to a "pot" configuration, and even if the period of accommodation delay occurs during near adjustment, the configuration of the focal plane B is changed, so that the hyperopic defocus amount Df of the central area of the retina is reduced to Df ', and the corresponding area a region a where the retina is stimulated is reduced to a ' and the myopic defocus amount of the eyeball is maintained to be greater than the near-periphery of the retina is reduced to a's myopic defocus. Furthermore, when the user looks at a close distance, the visual picture of the human eye is mainly the fine visual perception of the Central visual field of the macular area of the retina, so that the increase of the myopic defocus amount at the periphery of the retina greatly can cause the reduction of the definition of the picture at the periphery of the human eye, but the visual perception of the user using the eye at the close distance cannot be influenced.

On the contrary, in the same way, when the distance is from near 0.4 meter to far 3 meters, the previous degree setting on the lens can lead the center and the periphery of the retina to generate more myopic defocus difference values, therefore, the second control unit is used for controlling the P0 area, the P1 area and the P2 area to progressively decrease the myopic defocus, so that the focal plane B is changed from a 'pot-shaped' form to a 'pan-shaped' form, and meanwhile, the form that the myopic defocus at the periphery of the retina of the eyeball is greater than the myopic defocus at the center is maintained. The control scheme is set to match with the daily distant eye habit of a person, namely, the pupil is expanded in physiological reflectivity when the person looks away, and a larger area of central and lateral clear visual pictures are needed in visual perception.

The above is only an example, for the distance objects at other distances, the control is performed according to the rule that the farther the distance is, the smaller the myopic defocus increment from the center of the retina to the periphery is, and the closer the distance is, the larger the myopic defocus increment is, but the definition of the visual center must be maintained anyway, as shown in fig. 8, in order to correct the basic conventional myopia, and in the case of a conventional preset range, such as the absence of a specific disease, such as accommodation lag (accommodation lag), and in addition, by applying the dynamic defocus control system of the present technology, for the P0 area in the center, the increase of the myopic defocus in the center of the retina should be ensured not to exceed +0.50D. By way of further example, if a patient with myopic progression incorporates accommodation lag, the system may be set to vary the myopic defocus increment > +0.50D in the P0 region at 0.4 meters of near distance to accommodate the condition requirements of such a particular situation.

As a preferred embodiment, the first control unit and the second control unit are configured such that the absolute value of the negative acceleration is larger than the absolute value of the positive acceleration under equal distance. Meanwhile, the change mode of the defocus amount of the peripheral area of the retina following the central area has characteristic linkage. That is to say: according to the physiological movement characteristics of human eyes, the physiological regulation movement speed of the lens-ciliary muscle from near to far and from near to far is different, because the ciliary muscle is easy to tense and difficult to relax when the eyes of people, especially children and teenagers, are tired to use the eyes during regulation. Specifically, referring to fig. 9, taking as an example a zoom speed in which the defocus amount variation is poor in the peripheral retina and the central region within a certain fixed region range (as in the above-described retina P1 and P2 regions of fig. 7): in the range of 0.33 m to 3 m, the variation range of the far-to-near defocus difference variation rate v is larger than that of the near-to-far defocus difference variation rate v'. As far as near, the defocus difference in the peripheral area changes at a faster rate than in the central area. Conversely, when the distance is close to the near, the defocus variation rate in the peripheral area is slower than that in the central area.

By the control system, the central part and the peripheral part of the retina are subjected to different dynamic myopic defocus stimuli in the process from far-looking to near-looking and from near-looking to far-looking, the occurrence probability and the area stimulus quantity of the hyperopic defocus quantity generated by the central part and the peripheral part due to the lens adjustment delay in the process from far-looking to near-looking are reduced, and the visual blurring perception caused by the overlarge difference value of the myopic defocus quantity generated by the central part and the peripheral part due to the lens adjustment relaxation delay in the process from near-looking to far-looking is reduced. Meanwhile, the form that the myopic defocus amount at the periphery of the retina of the eyeball is larger than the myopic defocus amount at the center is maintained. On the other hand, the control of the change rate of the myopic defocus difference from the center to the periphery of the retina can also provide a novel myopia optimization control means. The problem of traditional out-of-focus lens can't effectual correction because of the retina central authorities that the eyeball physiological regulation dynamic change produced or peripheral hyperopia out-of-focus stimulation that still probably exists, or myopia out-of-focus volume is not enough is solved, can slow down the axis of the eye by the at utmost and lengthen, slow down myopia and deepen.

As a preferred embodiment, referring to fig. 6, when the distance is switched to the object, the position of the optical center is often changed, for example, when the eyeball is suddenly switched from the blackboard at the distance of looking at the object to the blackboard at the distance of looking down, the optical center needs to be moved down. Therefore, in the present embodiment, the dynamically controlled out-of-focus myopia correction system further includes a tracking module 7 for tracking the visual center position of the eyeball of the user, the tracking module 7 is connected with the control module, and the control module includes a positioning unit for positioning the optical center axis X of the dynamically out-of-focus lens 5 according to the visual center position and maintaining the optical center axis X at the visual center position. The tracking module 7 tracks the sight direction of the user along with the rotation of the eyeball, changes the distance sensed by the sensing module 6, calculates the visual center position by using the central arithmetic unit 8, and sends the visual center position to the control module, and the control module obtains the corresponding optical center position O on the dynamic out-of-focus lens 5 through calculation and comparison. As shown in fig. 6, the upper picture is that the eyeball gazes at the distant object horizontally, the lower picture is that the eyeball gazes at the near object downward, and during the process of switching the distance to the near object, the optical center position O moves downward along with the line of sight, and the distance power of the lens is controlled by taking the optical center position O as the center. In order to take account of the structure feasibility and improve the control accuracy, the peripheral area is divided into at least two sections of peripheral defocus rings with increasing diameters from inside to outside in sequence, as shown in fig. 10 and 11, the dynamic defocus lens 5 in the figure comprises a central area 51 and two sections of peripheral defocus rings 52, the central area 51 and each section of peripheral defocus ring 52 are used as control areas independently during control, and the more the sections are, the higher the control accuracy is.

In a preferred embodiment, referring to fig. 14, the dynamic out-of-focus lenses are in two groups, which are respectively used by the left and right eyeballs of the user, and comprise a left lens 51 for the left eye ball of the user and a right lens 52 for the right eye ball of the user, and the first control unit and the second control unit are respectively connected with the two groups of dynamic out-of-focus lenses and can alternatively or simultaneously control the two groups of dynamic out-of-focus lenses.

Specifically, the method comprises the following steps: the left lens 51 is worn by a left eyeball, the right lens 52 is worn by a right eyeball, and due to the characteristic of binocular fusion image complementation when two eyes watch simultaneously, the defocusing form and the speed of one lens can be independently and intensively controlled according to clinical needs. For example: the visual quality of an eyeball is slightly reduced, but the myopic defocus is made faster and larger, a steeper focal plane change is obtained, so as to make a signal for stimulating the eye axis of the eyeball to develop slowly, and a user can not feel the visual difference in the process of using the eyes generally, because as long as the vision of one eye is seen clearly, the visual pictures of two eyes can keep the vision of the two eyes clear in a way of fusion complementation. For example, theoretically, in the far and near vision, the control system can always make the defocus difference in the central area of the retina between the two eyes between +0.25D and +1.25D, or make the visual difference between the left and right eyes less than or equal to 2 rows of visual chart (taking the E visual chart standard as an example), so that the influence of the binocular vision perception is small on the basis of the visual fusion, and the control of the myopia axis development delay can be considered. Furthermore, the dynamic defocus gradient difference of the two eyes can be the rate change of the dynamic smooth gradient flicker, or the dynamic defocus gradient flicker tends to be continuously fixed for one eye (for example, the myopic degree of one eye is deepened more rapidly, and the development of the ocular axis needs to be intensively interfered), or the left eye and the right eye are alternately switched.

An ophthalmic device for controlling dynamic retinal defocus can be invented based on the above dynamic retinal defocus control system, and comprises the above dynamic retinal defocus control system.

Specifically, the method comprises the following steps: the ophthalmic device can be used for correcting myopia, the glasses can be made into a corneal contact lens to be worn by a user, and the control module is in control connection with the corneal contact lens in a wireless connection mode. The glasses can also be made into frame glasses, and the control module and the lenses are arranged on the glasses frame.

The ophthalmic apparatus may also be a vision training device for training myopia correction, as shown in fig. 15, the vision training device further comprises an eyepiece 93 for near-eye display of the user, a display 91 for providing a virtual image, and a single-focus Variable-focus element (VFE) 92 for switching between far view and near view of the virtual image, in addition to the above dynamic retinal defocus control system, wherein the eyepiece 93, the dynamic defocus lens 5, the VFE 92 and the display 91 are sequentially arranged on the same axis at intervals. Wherein the eyepiece 73 is designed with a fixed focal length between +20D and +10D, so that human eyes can see the close-range picture in the visual training device clearly under the condition of the close-range relaxed crystalline lens, and the VFE component 92 provides a dynamic single-focus zoom amount in a wide range, mainly used for inducing the adjustment movement of the crystalline lens, and the range is-20.00D to +2.00D. The dynamic defocus lens 5 mainly provides different defocus changes for each region of the intraocular retina in greater detail. The display 91 provides far and near pictures of virtual objects, the VFE component 92 simultaneously provides physical optical focal length to stimulate eyeball ciliary muscles to perform accommodation movement, the accommodation sensitivity can achieve the purpose of exercise, and the dynamic out-of-focus lens 5 provides dynamic myopic out-of-focus stimulation to the retina, so that myopia is delayed and controlled, and the problems of visual fatigue or abnormal visual function adjustment are solved. Preferably, since the vision training device can also perform the function of myopia retardation training by performing training on a fixed fixation target, in order to simplify the structure and control procedure of the vision training device, the dynamic retinal defocus control system and the VFE assembly 92 may be set to be an interlocking structure, so that the VFE assembly 92 is interlocked according to the controlled zoom amount without performing vision tracking, distance sensing, optical center movement positioning, and the like. Of course, the above is just a preferred embodiment, the dynamic retinal defocus control device can also be combined with other visual devices to realize function superposition, for example, CN107526165B discloses a visual display device technology, according to various diopters dynamically provided by a diopter adjusting unit, the user's eyes can perform physiological adjustment movement accordingly to clearly view the image displayed on the fixed display surface, so as to alleviate eye fatigue, wherein the diopter adjusting unit provides various diopters to the user's eyes according to the user's personalized physiological adjustment requirement characteristics for viewing, and the diopter adjustment provides correction of the content image in combination with the retinal imaging magnification variation perceived by the user's brain. The dynamic retinal defocus control device of the invention is combined with the device of the patent to form a functional myopia delaying trainer.

The above are only some application examples of the dynamic retinal defocus control system, and the dynamic retinal defocus control system can also be used for clinical requirements in other specific situations, adjusting the defocus difference change rate of each area of the retina, and being applied to diagnosis and treatment equipment such as visual function abnormality, visual training rehabilitation before and after refractive surgery, adjusting function exercise of presbyopia, other complicated ametropia, and strabismus and amblyopia visual training without departing from the spirit and characteristics of the invention.

While the present invention has been described in detail and with reference to the embodiments thereof as shown in the accompanying drawings, it will be apparent to one skilled in the art that various changes and modifications can be made therein. Therefore, certain details of the embodiments are not to be interpreted as limiting, and the scope of the invention is to be determined by the appended claims.

Claims

1. A dynamic retinal defocus control system, comprising:

a control module, the control module comprising:

2. The dynamic retinal defocus control system of claim 1 wherein the first control unit ensures that the amount of myopic defocus at the center of the retina is increased by not more than +0.50D when controlling the dynamic defocus lens to increase the spherical power, and the second control unit ensures that the amount of myopic defocus at the center of the retina is increased by not more than +0.25D when controlling the dynamic defocus lens to decrease the spherical power.

3. The dynamic retinal defocus control system of claim 1, wherein the first control unit and the second control unit are set such that the absolute value of the negative acceleration is larger than the absolute value of the positive acceleration in the case of equal distance.

4. The dynamic retinal defocus control system as recited in claim 1, further comprising a tracking module for tracking a visual center position of an eyeball of a user, the tracking module being connected to the control module, the control module comprising a positioning unit for positioning an optical center axis of the dynamic defocus lens in accordance with the visual center position and maintaining the optical center axis at the visual center position.

5. The dynamic retinal defocus control system of claim 1, wherein the dynamic defocus lens includes a plurality of microlenses in a dense regular arrangement, and each of the microlenses can be individually activated and adjusted in power by the control module.

6. The dynamic retinal defocus control system of claim 1, wherein the dynamic defocus lens is a bionic flexible lens with an eyeball lens structure, and the control module is configured to adjust the power of different areas of the dynamic defocus lens by means of deforming the bionic flexible lens through dynamic stretching.

7. The dynamic retinal defocus control system as claimed in claim 1, wherein the dynamic defocus lenses are provided in two sets for the left and right eyes of the user, respectively, and the first control unit and the second control unit are connected to the two sets of dynamic defocus lenses and can control the two sets of dynamic defocus lenses alternatively or simultaneously.

8. An ophthalmic apparatus for dynamic retinal defocus control, comprising the dynamic retinal defocus control system according to any one of claims 1 to 7.

9. A dynamic retinal defocus control method is characterized by comprising the following steps:

sensing the far and near focal length change of an object viewed by eyeballs of a user by using a sensing module;

acquiring sensing information of the sensing module by using a trigger unit and judging the sight state of eyeballs of a user according to the sensing information:

when the user looks from far to near, the first control unit is triggered to work, the first control unit controls the dynamic defocusing lens to increase the positive sphere power from the optical peripheral area to the optical central area at a negative acceleration, and the form that the myopic defocusing amount at the periphery of the retina of the eyeball of the user is larger than the myopic defocusing amount at the center is maintained;

and when the user judges that the user looks from near to far, the second control unit is triggered to work, the second control unit controls the dynamic out-of-focus lens to decrease the spherical power from the optical peripheral area to the optical central area at a positive acceleration, and the form that the near-sighted out-of-focus amount at the periphery of the retina of the eyeball of the user is larger than the near-sighted out-of-focus amount at the center is maintained.

10. The dynamic retinal defocus control method of claim 9, wherein:

tracking the visual center position of the eyeball of the user by using a tracking module while sensing by using a sensing module;