RU2283066C1 - Artificial eye lens possessing dosed intraocular focal power changes - Google Patents

Abstract

FIELD: medical engineering.

SUBSTANCE: device has ring-shaped haptic part having two external diametrically opposite projections in its principal plane manufactured as a whole with it as flat spirals bent to the same side and the optical part. The optical part has single or two lenses. The haptic part has three internal ring-shaped grooves forming ring-shaped projections. Through opposite slits are available on the second and the third frontal projection relative to cornea. The slits are congruent to projections of each lens and serve as means for placing a lens on one of the ring-shaped projections. The internal ring-shaped grooves allow the lens projections to move in them. The through slits on the frontal and the third ring-shaped projections are arranged one under the other. The through slits on the second ring-shaped projection are arranged between those three through slits. Non-penetrating opposite holes are available in peripheral part of the frontal surfaces each of the lenses to enable lens rotation by moving their projection members in the ring-shaped groove of the haptic part.

EFFECT: reduced risk of traumatic complications.

3 cl, 7 dwg

Description

The invention relates to medicine, more specifically to ophthalmology, and can be used for intraocular changes in the optical power of the artificial lens of the eye (IHG) in the postoperative period with additional correction of ametropia.

The need for a metered intraocular change in the optical power of ICH arises in situations where it is difficult to predict the final parameters of the eye, a high probability of induced ametropia, or a planned change in clinical refraction in the postoperative period is necessary. This need arises with a dynamic change in the optical parameters of the eye (for example, intraocular correction in childhood, since the natural growth of the eye lasts on average 10 years or more), with intraocular correction against the background of a forced change in the refractive power of optical media, for example, due to the introduction of indefinitely vitreous substituting fluids into the vitreous cavity in the case of cataract extraction and implantation of IHG with high myopia, when the true definition for our eyes are difficult due to the possible presence of staphylus sclera, in the case of an eye condition after refractive surgery, when it is difficult to obtain a standardized value of corneal refraction, in the presence of temporary ametropic refraction to eliminate anisometry, as, for example, in the case of intraocular correction in one eye with the initial bilateral ametropia of one degree until the moment of the need for intraocular correction in the paired eye.

The closest analogue of the claimed invention is a well-known artificial eye lens with a metered intraocular change in optical power, containing the haptic part in the form of a ring placed in its main plane, made for one with two external opposite protrusions in the form of flat spirals, bent to one side, and interchangeable the optical part with two opposite protrusions made in one in the form of curved figures for fixing in the haptic part (see WO 2005/013850 A2, A 61 F 2/16, 17.02 / 2005, 8 l.).

However, in the presence of residual ametropia in the postoperative period after implantation of IHG when replacing the optical part, there is a high probability that rupture of the zinc ligaments or capsule bag, which have a very delicate structure, can occur.

An object of the invention is the creation of an IHG design for the purpose of intraocular correction of ametropia in the postoperative period in order to reduce trauma when replacing the optical part.

The specified technical problem, according to the invention, is solved by the fact that in IHG with a metered intraocular change in optical power, containing the haptic part in the form of a ring with two external opposite protrusions in the form of planar curved figures bent in one one side, and a replaceable optical part with two opposite protrusions made in one with it in the form of flat curved shapes for fixing in the haptic part, the optical part is made in the form of one one or two lenses with flat protrusions, and the haptic part is made with three inner annular grooves forming annular protrusions; on the front of the cornea, the second and third annular protrusions, through opposite slots are made, congruent to the protrusions of each of the lenses, for placing the lens on one of these annular protrusions, and the inner annular grooves are configured to move the protrusions of each of the lenses in them; in this case, the through slots on the front and third annular protrusions are respectively arranged one below the other, the through-slots on the second annular protrusion are located respectively between the through-slots, and non-through opposite holes are made on the periphery of the front surface of each lens for rotating the lens by moving its protrusions in the annular groove haptic part.

The protrusions of each of the lenses are located in the main plane of the lens, with each protrusion of each of the lenses made with a groove congruent to the edge of the annular protrusion of the haptic part, forming two flat curved protrusions lying in planes parallel to the main plane of the lens and located on different sides from her.

According to the invention, in the postoperative period, the proposed IHG with interchangeable optics allows a metered intraocular change in its optical power due to the fact that the optical part is made with the possibility of reciprocating motion along the optical axis (to the cornea or retina) by changing the fixation of the lens protrusions on a certain annular protrusion ring lenses according to the correction of ametropia.

The invention is illustrated by drawings, where Fig. 1 (a top view and a side view) shows a lens 1 of the optical part of the IHG with opposite protrusions 2, 3 lying in its main plane and made integral with it, and with non-through opposing openings 4, 5.

Figure 2 shows (top view and side view) the second lens 6 of the optical part of the IHG with opposite protrusions 7, 8 with grooves 9, 10 and with non-through opposing holes 11, 12.

Figure 3 shows the haptic part of the IHG (a top view and a section along AA, and a bottom view) in the form of a ring 13 with inner annular grooves 14, 15 and 16, forming annular protrusions 17, 18, 19 and 20 with corresponding slots 21 and 22, 23 and 24, 25 and 26, and there are no slots on the last protrusion 20, as well as protrusions 27, 28 of the haptic part in the form of flat spirals.

Figure 4 shows the IHG according to the invention (top view and section BB), which shows the optical part: lens 1 and lens 6, the haptic part in the form of a ring 13, protrusions 2, 3 of the lens 1 are fixed on its inner annular protrusion 18; and in the grooves 9, 10 of the lens 6, the edge of the annular protrusion 19 of the haptic part is fixed. In this case, the protrusions 2 and 3, 7 and 8 of each lens 1, 6 are fixed between the through slots 21 and 22, 24 and 23 25 and 26 on the annular protrusion 17, 18, and 19 of the haptic part.

Figure 5 shows the IHG (a top view and a section along CC), for example, with one lens 1 in the ring 13 of the haptic part, its protrusions 2, 3 are fixed on the annular protrusion 18.

Figure 6 shows the IHG (top view and section along DD) according to the invention, for example, with one lens 6 in the ring 13 of the haptic part, the edge of the annular protrusion 19 of the ring 13 of the haptic part is fixed in its grooves 9, 10.

The placement of lenses 1 and 6 in the ring 13 of the haptic part is as follows.

First, the protrusions 7, 8 of the lens 6 are placed in the through-cuts 21 and 22 of the annular protrusion 17 and lower it onto the protrusion 18, then with the help of through holes 11, 12 they deploy this lens until they are located in the holes 23, 24 of the annular protrusion 18 of the ring 13 of the haptic part and lower on the annular protrusion 19 of the ring 13, and fix the edge of this protrusion, respectively, in the grooves 9, 10 of the protrusions 8, 7 and between the slots.

Then, the protrusions 2, 3 of the lens 1 are similarly placed in the through-slots 21, 22 of the annular protrusion 17 and lower it on the protrusion 18 of the ring 13 of the haptic part, and fix the protrusions 2, 3 on this protrusion, placing them between the through-cuts and above the protrusions 7, 8 lenses 6.

Dosed intraocular correction of optical power is as follows. For intraocular correction of myopia, either (Fig. 4) the lens 6 is moved deeper, or when myopia is corrected, lens 1 is removed to a greater extent if it has been implanted, or it is replaced by a lens of lower optical power, or lens 1 of the corresponding positive or negative optical power is implanted.

For intraocular correction of hyperopia, either Lise 6 is moved toward the cornea (Fig. 6), if there is no lens 1, or lens 1 (Fig. 4) is added with the corresponding positive optical power, or it is replaced with a lens with higher optical power.

For intraocular correction of anisometropia, either reduce the refraction of the eye by moving lenses 1, 6 and / or 4 from the cornea or by replacing the lens with a lower optical power, or implant the lens 1 of the corresponding positive / negative optical power, or increase the refraction of the eye by moving the lenses 6 and / or 1 to the cornea, either by replacing the lens with a higher optical power, or implanting lens 1 of the corresponding positive optical power.

For intraocular correction of induced anisometropia, either reduce / increase eye refraction through the actions described above, or perform these actions in accordance with changes in refraction in the paired eye, or, with bilateral implantation, perform coordinated actions for intraocular correction in both eyes.

Implantation of IHG is as follows.

After phacoemulsification, the anterior chamber and capsule bag are filled with viscoelastic. Through the tunnel section using the injector or in the folded state, the haptic part of the IHG is introduced into the anterior chamber, the capsular bag. Then, also using the injector or in the folded state, the optical part of the IHG is introduced into the front chamber. Assembly of IHG is performed intraocularly. The anterior chamber is washed with a BSS solution, a solution of acetylcholine 0.01% is introduced. The operational access is sealed by hydration.

The proposed IHG works as follows. Moving the lenses 6 and / or 1 from / to the cornea reduces / increases the optical power of the IHG. Adding a positive / negative lens 1 increases / decreases the optical power of the ICH. Replacing the lens 6 and / or 1 with a larger / smaller value of the optical power increases / decreases the optical power of the IHG. The magnitude of the displacement and the value of the optical power of the inserts are calculated according to the mathematical dependence on the basis of the magnitude of the required dosed intraocular correction.

The optical power of the replaced optical part is calculated according to the mathematical dependence on the basis of the magnitude of the required dosed intraocular correction.

The work of IHG in the postoperative period, if necessary, a metered intraocular change in the optical power of IHG: through a performed corneal paracentesis, 1% mesatone solution is injected into the anterior chamber to achieve maximum mydriasis. The anterior chamber is filled with viscoelastic. Using technological holes 4, 5 or 11, 12 on lens 1 or lens 6, it is biased towards the cornea or retina to attenuate or enhance clinical refraction by placing them on the corresponding annular projections 17, 18, 19, or 20 according to the required amount of ametropia correction .

IHG with a dosed intraocular change in optical power is implanted through the incision used for phacoemulsification, firmly fixed in the capsule bag, occupies a stable position, replacement of the optical part is accompanied by minimal trauma, change in optical power can be predicted and dosed, and the replacement of the optical part is not accompanied by the risk of development complications encountered with intraocular correction (pupil block, IOL displacement, etc.).

If necessary, achieving the desired effect of the lens (6.6a) can be located on the protrusions 17 and 19 of the ring 13 of the haptic part of the IHG (Fig.7) or on the protrusions 19.20 (not shown in Fig.).

In addition, the ratio of the maximum height H of the ring 13 of the haptic part to its maximum outer diameter D can be no more than 0.43.

The IHG according to the invention is made of a biocompatible, flexible material with the possibility of folding for implantation through small incisions and in injectors.

Claims (3)

1. An artificial lens of the eye with a metered intraocular change in optical power, containing the haptic part in the form of a ring placed in its main plane, made for one with two external opposite protrusions in the form of flat spirals bent in one direction, and a removable optical part with two opposite protrusions made in one with it in the form of curvilinear figures for fixing in the haptic part, characterized in that the optical part is made in the form of one or two lenses with flat protrusions, and g the aptic part is made with three inner annular grooves forming annular protrusions, on the front of the cornea, the second and third annular protrusions, through opposite slots are made, congruent to the protrusions of each of the lenses, for placing the lens on one of the indicated annular protrusions, and the inner annular grooves are made with the ability to move the protrusions of each of the lenses in them, while the through-cuts on the front and third annular protrusions are located one below the other, respectively, the through-cuts on W A second annular protrusion is located respectively between these through-cuts, and non-through opposite holes are made on the periphery of the front surface of each lens for rotation of the lens by moving its protrusions in the annular groove of the haptic part. 2. The artificial lens according to claim 1, characterized in that the protrusions of each of the lenses are located in the main plane of the lens. 3. The artificial lens according to claim 1, characterized in that each protrusion of each of the lenses is made with a groove congruent to the edge of the annular protrusion of the haptic part, forming two flat curved protrusions lying in planes parallel to the main plane of the lens and located on different sides of it .

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