HU181900B - Ophthalmologic optical system and method for measuring the refraction thereof, furthermore frame thereof - Google Patents

Abstract

The invention relates to a visual aid for the distance and Nahsichtbereich. The aim and object is to have available a distortion-free ophthalmic optical system with a sliding diopter number which has a large field of view angle and a low mass and whose lenses are easy to manufacture and to measure. The inventive system includes an optical lens having a spherical front refractive surface and a rear refractive surface which is described by a second order equation. The lens thickness decreases from the lower edge to the upper. The eyeglass frame for this system has frame rings formed by two segments. A segment is used for installation d. thin lens edge. D. Frame racks have Buegel u. are connected by a saddle bridge bent in the opposite direction to the bowing direction. The measurement of the lens is carried out by focusing an observation telescope on an object, arranging the lens between the observation telescope and the object, rotating the lens and determining its refraction by means of a calibration lens.

Description

FIELD OF THE INVENTION The present invention relates to optical systems, in particular to ophthalmic optical systems with increasing variations in refractive index in the vertical plane. The invention also relates to a method for measuring the refraction of this optical system, and to a frame of the optical system.

Most preferably, the present invention is used to correct refractive error, lack of adaptability of the eye, or old age, presbyopia, or aphakia.

In an ophthalmic optical system, the change in the optical refractive power of the lens required for presbyopia and aphakia is preferably continuous and must occur within the lens eye without any image jump and minimal distortion.

If the object is viewed through the upper part of the ophthalmic lens, an accurate imaging of the object in the pericardium of the eye should be observed in such a way that the person wearing the spectacles appears infinitely.

When the subject is viewed through the lower part of the ophthalmic lens, the image of the subject in the pericardium is now closer to the person wearing the glasses.

Thus, the ophthalmic ophthalmic power (diopter) of an ophthalmic optical system relative to the upper lens frame should be steplessly magnified2 with constant lifelike representation.

Refractive errors and adaptation deficiencies, e.g. in the case of presbyopia, there is a lack of adaptation, or in the case of aphakia, two glasses, the first of which corrects near-sightedness and the second of which corrects vision. To view objects in the intermediate space, e.g. if the person is traveling up or down stairs, it is desirable to use additional glasses with the refractive power set between the two glasses.

However, the use of three different glasses is extremely cumbersome and it is common for a person to swap the three glasses.

Instead of two glasses, an ophthalmic optical system with two lenses having different focal lengths, i.e. different refractive power, can be used.

The so-called bifocal ophthalmic optical systems are already widely known. They contain optical lenses that consist of parts with different focal lengths. One part, located on the underside of the optical lens, is needed to see nearby objects. This distance is 250-500 mm. The other part of the lens, which is located at the top, is used to view distant objects which, for example. They are between 2 meters and infinity.

If such ophthalmic optics are worn, the distance between 500mm and 2m will practically fall out of line of sight, which will impair the ability of the eye to adapt. In modern life, however, it is this intermediate domain that plays a major role, for example. it is about driving a car or looking at shop windows, machines, or when the person is up or down stairs.

In addition, said ophthalmic optical system is characterized in that the change in refractive power in the vertical plane is abrupt, with the result that image jumps besides image doubling are also disadvantageous due to abrupt changes in image size.

The loss of the distance between 500 mm and 2 meters from the field of vision can be prevented by using an optical system for the glasses, each lens consisting of three parts with different refractive power.

Tri-focal optical ophthalmic lenses are already known. One part of such a glass is used for imaging objects infinite to 2 meters from the person wearing the glasses, the other part of the lens is for imaging objects 2 meters and 500 mm from the person wearing the glasses, and the third part of the lens provides visualization of objects at distances of 500 mm and 280 mm to the peritoneum. The disadvantage of these glasses, however, is that they have transient stages, which cause interfering reflections. At each transition site, the eye's visual acuity is lost in the angular range of 7-10 ° for the two gears because of the different refractive power of adjacent lens portions. This range of vision is reduced by 20% by this optical system.

In said trifocal ophthalmic optical systems, the change in refractive power in the vertical plane is abrupt, which is disadvantageous.

It is possible to form an ophthalmic optical system in the vertical plane with a continuous change in refractive power if the lenses are formed with complex aspherical surfaces.

Such an ophthalmic system is disclosed in U.S. Patent No. 3,950,082. U.S. Pat. No. 4,123,195, which has at least one lens made of light-transmitting optical material on the front and rear refractive surfaces.

In the geometric and optical sense, the continuous refractive surface is aspherically formed, has two intersecting main orthogonal planes, and is characterized by a cross-section of the lens having a conic section having an eccentricity greater than or slightly different from zero.

In this embodiment, starting from the upper part of the lens, a constant increase in the value of the refractive force towards the lower part of the lens is achieved by continuously increasing the curvature of the front surface from the upper end of the lens to the lower part of the lens. The rear surface of the lens can be described by a quadratic equation.

With this solution, a smooth and continuous change in the refractive power of the ophthalmic optical system can be achieved without image jump.

However, these glasses are extremely expensive and require special equipment and equipment to make them.

Different cone sections with different fracture forces represent a distorted image on the retina of the eye.

Ophthalmic optic systems may be housed in a frame having peripheral portions securing the optical system, interconnected by a seam, and having a stem secured to the periphery of the frame. According to the shape of the optical lenses, oval, round, pantoscopic, horseshoe-shaped and roof-tile-shaped rim portions are produced. The most commonly used are the oval and round edges.

However, the structure of these frames does not permit the recording of ophthalmic optical lens systems whose dioptric number varies continuously in the vertical plane.

One frame solution for capturing continuously changing diopter ophthalmic lens systems in the vertical plane is disclosed in U.S. Pat. No. 3,958,867. The patent states that the frame parts for fixing the optical lenses are connected to each other by a seam and have stems which are fixed to the edge portions of the frame. The frame edges are provided with annular grooves. The frame edges are provided with additional elements, the protruding part of which is made of elastic material.

These protrusions extend into the corresponding grooves of the frame periphery.

Although the ophthalmic optical system, which has a continuously changing diopter in the vertical plane, can be mounted within this frame, the construction is complicated and unreliable.

Only one lens can be attached to a single rim portion of the frame outlined above.

The value of the fraction of the ophthalmic lens should be measured when checking the ophthalmic optical lenses produced.

One solution for measuring the fraction of ophthalmic optical lenses is known from the US Patent No. 543,910. copyright certification, which focuses on focusing a telescope on an infinite object and adjusting a mark in the collimator's objective focal plane so that a sharp image of that mark appears in the focal plane of the telescope's lens, and then the glasses to be measured placed between collimator lenses such that the optical axis of the glasses coincides with the optical axis of the telescope. The optical lens to be examined is shifted along the optical axis so as to overlap the rear surface of this lens with the plane of focus of the collimator lens. The signal is then shifted on the optical axis until its sharp image appears sharply in the focal plane of the binocular lens, and the refractive power of the optical lens is determined by a dioptric scale. This scale is mechanically connected to the signal.

Since in this said method the optical lens has no possibility of rotation about a center of rotation, only conventional ophthalmic lenses can be controlled by this method.

This procedure, as well as the measurement of refraction, does not provide sufficient accuracy.

A method for measuring the refractive power of ophthalmic optical lenses is known, which consists in focusing a telescope on an object in infinity, and positioning the measurable optical lens between the telescope and the object such that one axis of the lens is aligned with the optical axis of the telescope. coincide. The signal displayed in the plane of focus of the collimator lens is adjusted so that the signal is sharply drawn in the plane of focus of the telescope lens. The collimator signal is then shifted relative to the collimator objective lens until the sharp image of the collimator appears in the plane of focus of the telescope lens. This signal is mechanically connected to a dioptric scale on which the refractive power of the lens being measured can be read.

To measure the refractive power of the second optical axis of the lens to be examined, the lens is rotated about a center of rotation, the axis of the optical lens being measured is overlapped with the optical axis of the telescope, and the refractive power of the lens is then determined.

This method has the disadvantage of not providing good measurement accuracy because the lens is still infinite when measuring the refractive power of the lens which is used to observe the object and is located at a distance from the observer.

Our goal is to design an ophthalmic optical system that requires simple technological conditions. The lens of the ophthalmic optic system of the present invention has a shape that allows the lens to be manufactured using conventional technology for forming ophthalmic lenses using conventional machine tools, and is intended to reduce the weight of the ophthalmic optical system, i.e., the lens weight. increase the viewing angle. It is a further object of the present invention to propose a new frame of simple structure for this lens and to propose a method for measuring refraction which allows rotation of the optical lens around the rotation point in such a way that very high measurement accuracy is achieved. ^-

SUMMARY OF THE INVENTION The object of the present invention is to provide an ophthalmic optical system according to the invention having a continuously varying refractive power in the vertical plane of the lens, having separate front and rear refractive power (diopter), the latter being defined by a quadratic equation. According to the invention, the front surface is a spherical surface arranged relative to the rear surface such that the thickness of the lens decreases from the lower frame portion to the upper frame portion so that the focal length of the ophthalmic optical system varies uniformly in the vertical plane and adaptation range.

The spherical shape of the front surface of the optical lens and the manner in which this surface is positioned relative to the rear surface, whereby the thickness of the optical lens decreases from the lower part of the frame to the upper part, creates a distance between the front surface of the optical lens and its focal point relative to the optical axis and in the direction of the main beam path.

The greatest difference between these distances, which corresponds to the lowest refractive index, can be achieved on the thin rim of the optical lens.

The design of an optical lens in an ophthalmic optical system such that the lens has a narrow rim at the top allows the observer to view objects through the optical system with the least refractive power (diopter).

Preferably, the ophthalmic optical system has another lens formed similarly to the first lens, the two lenses being mounted such that their optical axes coincide. The signs of refractive indices are always the same for both lenses.

The ophthalmic optical system consisting of two lenses is designed so that their optical axes coincide and the sign of the refractive power of both lenses is of the same magnitude in any section, whereby the opacity of the ophthalmic optical system is increased by the thickness of the two optical lenses. This total thickness is less than the thickness of an optical lens whose refractive power is equal to the sum of the refractive power of two lenses (a prerequisite being the presence of four refractive surfaces).

Preferably, in each ophthalmic optic system used for correction of presbyopia and hypermetropia, the optical axis runs beyond the center of the sagittal section and is located near the lower thick edge of the optical lens.

The positioning of the optical lens axis in the center of the sagittal axis of the lens and its proximity to the lower thick edge of the lens when applied to a positive refractive ophthalmic lens enables the lens to be shifted toward the lower thick lens, where high positive refractive power is required. for viewing nearby objects. In addition, a small positive refractive force is formed at the edge of the thin lens, which is required for viewing distant objects.

Preferably, in the ophthalmic optic system for presbyopia and alpha correction, the optical axis runs in the center of the sagittal section of the optical lens and in the middle of the upper edge of the optical lens and near the upper thin edge of the optical lens.

Shaping the optical lens so that the center of the sagittal section of the optical lens is near the thin upper edge allows the ophthalmic optical system having a negative diopter to be designed such that the optical lens axis is directed toward the upper thin lens frame. offset, provided that greater negative dioptery is required there, which is required for viewing distant objects. In addition, on the thick lens flange, the minimum negative refractive force required to observe distant objects is achieved.

Preferably, in an ophthalmic optic system for presbyopia and aphakia,

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Ί its optical axes are formed near the center of the sagittal axis of the optical lens near its thicker edge.

Positioning the optical lens axis above the center of the sagittal lens section near the lower thick lens flange ₅ allows the development of an ophthalmic optical system having a positive diopter, which can be shifted downstream of the optical axis of the lens when a high positive refractive force is required for viewing objects in the stone. In addition, the thinner lens edges provide the minimum refractive power required to view distant objects.

The object is solved by forming anterior and posterior refractive surfaces within an ophthalmic optical lens of continuously varying refractive power in the vertical plane. The rear fracture surfaces can be defined by a quadratic equation. The edges of the frame, in which the optical lenses 20 are disposed, are interconnected by a nose saddle, and this frame has stems which are attached to the edges of the frame. The essence of the invention is that the edges of the frame are formed of at least two segments, one of which is used to capture the thin edge of the optical lens. The nose saddle is bent in the opposite direction to the stem of the glasses and is positioned with the required angle of view. 30

The two-segment design of the eyeglass frame allows for insignificant replacement of the ophthalmic optical system fixed therein.

The orrnyeregnek bending in that direction, a direction opposite to the earpieces direction, and positioning the orrnyeregnek to the angle required size of the light provided by appropriate placement ₄₀ organize for the optical lens on the eye so that the inlet pupil of the ocular optical system of the eye rotation point overlay. This object is further achieved by placing two optical lenses 45 in the frame for mounting the ophthalmic optical system. The frame parts are interconnected by a nose saddle. The frame has stems that are connected to the frame. According to the invention, the frame has a segmental cross-section which is larger than the inside radius of the frame. At least two grooves are formed on the inner surface of each segment-shaped frame rim portion to hold the thinner edge of their respective optical lenses. These grooves are formed in the immediate vicinity of a plane running through a string segment perpendicular to the height of the segment. The nose saddle is bent in the opposite direction to the stem of the goggles and is positioned with the required angle of view. The height of the segment-shaped frames (having at least two grooves on the inside for gripping the thin edges of their respective optical lenses) is larger than the inside radius, so that the lenses can be replaced with insignificant force.

To accommodate the optical lenses, a groove is formed between the grooves in the immediate vicinity of a plane that runs perpendicular to the height of the segment through a string segment, which allows the optical lenses to be individually inserted into the frame due to the flexibility of the spectacle frame.

The insertion of optical lenses between the grooves in the immediate vicinity of a plane which runs through a segment string perpendicular to the height of the segment is provided with a groove which, due to the flexibility of the frame, allows the optical lenses to be individually mounted in the frame.

The object is further achieved by focusing the examination binocular on a subject during the process of measuring ophthalmic optical lens refraction, positioning the optical lens to be measured between the object and the telescope, rotating the optical lens to be measured about a pivot point, and then rotating the lens. we measure the refractive power to determine the refraction. According to the invention, after the optical lens to be measured is positioned between the telescope and the object, the center of the telescope's entry pupil is overlapped by the pivot point of the optical lens to be measured and rotated to the thickness of the optical lens to be measured corresponds to the difference between objects. The refractive force is then measured by compensating the refractive power of the lens to be measured with a calibration lens so as to obtain a sharp image in the focal plane of the binocular lens. Moving the pivot point of the optical lens to be measured and the center of the telescope's entry pupil, and the ability to rotate the optical lens to be measured up to a thickness corresponding to the distance of the front surface from the object, increases the accuracy of optical lens refraction measurement. are in natural conditions.

The invention will now be described in more detail with reference to the drawings. In the drawings it is

Figure 1 is a schematic cross-sectional view of an ophthalmic optical lens of the invention, a

Figure 2 is a schematic sectional view of an embodiment of an ophthalmic optical lens according to the present invention;

Figure 3 is a schematic cross-sectional view of another embodiment of an ophthalmic optical lens of the present invention,

Figure 4 is a schematic cross-sectional view of a further embodiment of an ophthalmic optical lens of the present invention,

Fig. 5 is a diagram depicting the height of the entrance pupil of the ophthalmic lens system of the present invention, showing a spherical deviation of this lens system along the longitudinal axis,

Figure 6 is a diagram illustrating the magnitude of the curvature of a vertical and sagittal image of this optical system as a function of the field of view of the ophthalmic lens system of the present invention;

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Fig. 7 is a diagram illustrating the dependence of the spherical deviation of the ophthalmic optical lens system of the present invention and the transverse distance from the size of the exit pupil, expressed in rad, based on the maximum field of view of this lens system;

Fig. 8 is a diagram similar to Fig. 7, based on a view angle smaller than the maximum, a

Fig. 9 is a diagram similar to Fig. 8, wherein the angle of view according to the invention is zero, a

Fig. 10 is a schematic front view of a frame for an ophthalmic optical system according to the invention,

Figure 11 is a sectional view of Figure 10 taken along lines XI-XI;

Figure 12 is a top view of Figure 10, a

Figure 13 is a schematic front view of an exemplary embodiment of a frame according to the present invention for an ophthalmic optical system;

Figure 14 is a schematic top view of Figure 13, a

Figure 15 is a schematic side view of Figure 13, a

Fig. 16 is a schematic front view of another embodiment of a rack for the ophthalmic optical system of the present invention,

Figure 17 is a sectional view taken along line XVII-XVII of Figure 16, a

Figure 18 is a schematic top view of Figure 16, a

Figure 19 schematically illustrates a method for measuring refraction of an ophthalmic optic lens system schematically based on an object located within the most preferred field of view of the lens, e.g. At a distance of 250 mm, a

Figure 20 is a schematic view of a method for measuring refraction of an ophthalmic optical lens system for an object located in infinity.

Our ophthalmic optical system with continuously varying refractive power has an optical lens 1 in the vertical plane (see FIG. 1) having a front spherical fracture surface 2 having a radius of curvature R1, a rearward fracture surface 3 defined by a quadratic radius R ₂ (C 1 and C _{2 are} the centers of curvature of the front and rear fracture surfaces 2 and 3), while R 1 = R ₂ equals the tip of the optical lens 1.

The thickness of the optical lens 1 is constantly decreasing.

The optical axis of the optical lens 1 passes through the thick rim of the optical lens 1 and the center of the sagittal section of the optical lens 1.

The 4 entry pupils of the ophthalmic optical lens are at a distance that allows for correction of system deviation (astigmatism) and is comfortable for the wearer of the glasses.

The main beam passes through the center of the inlet pupil 4 of the ophthalmic optic system and through the thin rim of the optical lens 1.

The β angle between the main beam path and the optical axis is the viewing angle of the ophthalmic optical system.

The aforementioned ophthalmic optic system is used to correct presbyopia.

In the exemplary embodiment shown in Fig. 2, the ophthalmic optic system has an optical lens 5 having a front spherical refractive surface 6, a radius of rotation R1 and a rear refractive surface 7 defined by a quadratic equation Has a radius of curvature of ₂ , so that the radius of curvature of R ₂ is much greater than that of R! radius of curvature (where C 1 and C _{2 are} the centers of curvature of the front and rear breaks 6 and 7 respectively).

The optical axis passes through the thin rim of the optical lens 5 and the center of the sagittal section of the optical lens 5.

The 8 exit pupils of the ophthalmic optical system are at a distance that allows for correction of the optical system deviation and is comfortable for the person wearing the glasses.

The main beam passes through the center of the 8-step pupil of the optical system and the thin rim of the optical lens 5.

The 0-angle of view between the main subject-side radiation path and the optical axis represents the field of view of the ophthalmic optical system. The ophthalmic lens outlined above is used to correct hypermetropia and periopia.

In the embodiment shown in Figure 3, the optical lens 9 of the ophthalmic optical system is configured to have an anterior spherical fracture 10 having a radius of curvature Rj, and a posterior fracture surface 11 having a quadratic equation R ₂ . where R! ¥ = radius of curvature R ₂ (the front and rear fractures 10 and 11 have centers of curvature C ₁ and C ₂ ).

The optical lens 9 runs above the thin rim portion in the center of the saggital section.

The 12 exit pupils of the ophthalmic optical system are spaced at a distance that allows for correction of the optical system misalignment and is comfortable for the wearer of the glasses.

The main beam passes through the center of the 12 outgoing pupils of the ophthalmic optic system and the thick rim of the 9 optical lenses.

The 0-angle of view between the main beam and the optical system represents the field of view of the ophthalmic optical system. This ophthalmic optical system is used to correct myopia and presbyopia.

In the exemplary embodiment shown in Figure 4, the ophthalmic optical system has an optical lens 13 having a front spherical fracture surface 14, a rear spherical fracture surface 15, and an optical lens 16 having a front spherical fracture surface 17 and a rear fracture surface 18. The latter rear breaking surface 18 can be defined by a quadratic equation. The front and rear refractive surfaces 14 and 15 of the optical lens 13 have a radius of curvature R ₂ , R ₂ (the front and rear refractive surfaces of the optical lens 13 have centers of curvature C ₂ and C ₂ ). The front lens 16 and posterior 17, 18 surfaces of the crusher are radii of curvature _R3 and R4. The front lens 16 and posterior 17, 18 surfaces of the crusher there are centers of the C _3, C ₄ of curvature. The thickness of the optical lenses 13 and 16 decreases continuously from one edge of the frame to the other.

The optical axis of the ophthalmic optic system passes through the thick rim of the optical lens 13, 16 and in the center of the sagittal section.

Optical lenses 13, 16 have a maximum thickness of 5 mm at the top and below.

The 19 outgoing pupils of the ophthalmic optical system are at a distance that allows for correction of system deviation and is comfortable for the wearer of the glasses.

The main subject-side radiation passes through the center of the outgoing pupil 19 of the ophthalmic optic system and through the thin rim of the optical lenses 13 and 16 respectively. The β-angle between the main subject radiation and the optical axis represents the viewing angle of the ophthalmic optical system.

In this ophthalmic optical system, the refractive power of the lenses is the same sign in any section.

The outlined optical system is used to correct presbyopia and severe hypermetropia as well as aphakia.

1, 2, -3, and 4, the center of the outgoing pupil overlaps the eye's pivot point when using any optical system. The refractive power of the lens portion for viewing the infinite object may be selected such that the posterior focal point of this lens portion is overlapped with the distal point of the eyelet which, by virtue of its own optics, is attached to the ocular nerve and it is selected so that the posterior focal point of the lens portion overlaps the proximal point of the eye, the proximal point of which is attached to the optic nerve due to ophthalmic optics. Hereinafter, embodiments of our ophthalmic optical system having continuously variable refraction values in the vertical plane will be described.

'25

Example 1

The refractive power of the ophthalmic optical system of Fig. 1 in the vertical plane varies continuously between + 0.2-2.7 dpt. This optical system is used to correct presbyopia.

The radius of curvature of the front refractive index of the optical lens The radius of curvature of the rear refractive index of the optical lens The thickness of the optical lens is constantly changing in the following range: refractive index on the axis (d ₀ = 5 mm)

R1 = 25.0 mm

R ₂ = 25.0 mm d = 0.5 + 5.0 mm r o = 1.6568 + 2.7 dpt β = 80 °

The front and rear refractive planes of the optical lens are spherical.

Example 2

The ophthalmic optical system (see Figure 1), which has a continuously varying refractive power in the vertical plane of -0.3 + +3.9 dpt, is used to correct presbyopia.

The radius of curvature of the front refractive index of the optical lens The radius of curvature of the rear refractive index of the optical lens is the range of continuously varying thickness of the optical lens in the refractive index on the axis (d ₀ - 6 mm). angle of view

R1 = 22.0 mm

R ₂ = 22.0 mm d = 0.5 + 6.0 mm r? D = 1.7440

3.9 dpt β = 80 °

The front and rear refractive surfaces of the optical axis are spherically formed.

.3. example

The ophthalmic optical system (see Figure 1) has a continuously variable optical refractive power of + 0.25 + 2.54 dpt in the vertical plane and is used to correct presbyopia.

The radius of curvature of the front refractive index of the optical lens over the rear refractive index of the optical lens The continuously variable range of thickness of the optical lens Refractive index on the axis (d ₀ = 5,0 mm)

R1 = 25.0 mm

R ₂ = 25.0 mm d = 0.5 + 5.0 mm t? D = 1.744 »2.54 dpt β = 80 °

The front and rear refractive surfaces of the optical lens are spherical.

It will be appreciated that, in the three embodiments described above, the front and posterior fracture planes of the optical lens, expressed in quadratic equations, are zero or eccentric or torus, respectively, to correct the astigmatic error of the eye.

Example 4

The refractive power of the ophthalmic optic system shown in Figure 2 in the vertical plane is continuously changing from < 3.8 to > 6.4 dpt for correction of presbyopia and hypermetropia.

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Radius of curvature relative to the front refractive index of the optical lens Radius of curvature relative to the rear refractive index of the optical lens Range of continuous change of the optical lens Refractive index of refraction on the axis (d ₀ = 6 mm)

The optical lens has a front spherical design.

R ₁ - 22.0 mm

R ₂ = 25.0 mm d = 0.5 + 6.0 mm r? D = 1.6568 +6.4 dpt β = 80 and rear fracture surface

Example 5

Fig. 2 is an ophthalmic optical system having a refractive power of +7 to +9 dpt in the vertical plane to correct presbyopia and hypermetropia.

Optical lens front radius of curvature relative to the refractive index relative to the rear refractive index of the optical lens- R1 = 22.0 mm radius of curvature R ₂ = 28.0 mm the process of the optical lens- range of tos _a d = 0.5 + 5.0 mm the refractive index »? D = 1.6919 breaking force on the shaft (d ₀ = 5 mm) +9.0 dpt angle of view β = 80 °

The optical lens has a front spherical design.

and rear fracture surface

Example 6

Figure 2 shows an ophthalmic optic system having a continuously varying refractive power in the vertical plane of 2.5 to 4.96 dpt for correction of presbyopia and hypermetropia.

The radius of curvature of the optic: lens front refractive index the radius of curvature of the rear lens refractive index is the range of continuous change of the optical lens refractive index on the axis (d ₀ = 6 mm)

R1 = 22.0 mm

R ₂ = 24.0 mm d = 0.5 + 6 mm tjd = 1.6126 + 4.96 * 5 dpt β = 80 °

The front and rear refractive surfaces of the optical lens are spherical.

It should be noted that in Examples 4, 5, and 6, the posterior refractive surface of the optical lens, which can be described by a quadratic function, is used to correct an astigmatic error of the eye having an eccentricity of 5 or torus with a value of zero or very close to zero.

Example 7

The ophthalmic optic system of Figure 3, which has a refractive power in the vertical plane of -2.5 to +0.4 dpt and is constantly changing, is used for presbyopia and myopia correction.

The radius of curvature for the front törőfelületére the optical lens for the posterior lens of the optical lens 20 törőfelületére continuously variable range of thickness of the refractive index in the axial törőerqe (d ₀ = 0.5) Viewing Angle

R1 = 22.0 mm

R ₂ = 20.0 mm d = 0.5 + 6.0 mm

7) D = 1.6126

-2.5 dpt β = 80 °

The front and rear refractive surfaces of the optical lens are spherical.

Example 8

An ophthalmic optic system of FIG. 3 having a continuously varying refractive power in the vertical plane of -6.3 to 2.7 dpt for presbyopia and myopia correction.

. .

Radius of curvature relative to the front refractive surface of the optical lens The continuously variable range of thickness of the optical lens over the rear refractive index 45 of the optical lens is the refractive index relative to the axis (d ₀ = 0.5)

R1 = 22.0 mm

R ₂ = 18.0 mm d = 0.5 + 6.0 mm? D = 1.6568 -6 _; 3 dpt β = 80

The front and rear refractive surfaces of the optical lens are spherical.

Example 9

The ophthalmic optical system of FIG. 3, having a continuously varying refractive power in the vertical plane of -4.6 to 0.9 dpt, is configured as follows for presbyopia and myopia:

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Optical lens front radius of curvature of its fracture R1 = 22.0 mm radius of curvature of the rear refractive surface of the optical lens R ₂ = 19.0 mm continuously varying thickness of the optical lens d = 0.5 + 6.0 mm the refractive index t? d = 1.6919 breaking force on the shaft (d ₀ = 0,5) —4.6 dpt angle of view 0 = 80 °

The front and rear refractive surfaces of the optical lens are spherical.

It will be appreciated that the posterior refractive surface of the optical lenses described in Embodiments 7, 8, and 9, described by a quadratic equation, has an eccentricity of zero or close to zero or a torus surface for additional correction of ocular astigmatism.

For the front refractive surface of the first optical lens

the radius of curvature of the first optical lens R1 = 22.0 mm 5 radius of curvature of the rearward fracture R ₂ = 26.0 mm the front refractive surface of the second optical lens _R3 = 22.0 mm the second optical lens 10 the radius of curvature of the rearward refractive surface is a function of the continuously varying thickness of the first and second optical lenses R ₄ = 26.0 mm 15 Justice between optical lenses d = 3.5 + 0.5 mm distance along the optical axis 0.5 mm 20 the refractive index t? d = 1.6919 breaking force on the shaft (d {, = 3.0; dl ¹ = 3.0) +13 dpt angle of view 0 = 80 °

Example 10

The front and rear fracture surfaces of each optical lens are spherical.

The continuous change in refractive power of the ophthalmic optic system shown in Figure 4 in the vertical plane is +13.6 to +11.5 dpt and serves for correction of aphachia.

The radius of curvature of the front refractive surface of the first optical lens The radius of curvature of the rear optical surface of the first optical lens The front refractive surface of the second optical lens The rear refractive surface of the second optical lens axis of view (d '= 3.0; dV = 3.0)

R ₁ = 22.0 mm

R ₂ = 27.0 mm

_R3 = 22.0 mm

R ₄ = 27.0 mm d = 3.0 * 0.5 mm

0.5 mm ηρ = 1.6568 +3.6 dpt = 80 °

The front and rear fracture surfaces of each optical lens are spherically formed.

Example 11

The ophthalmic optical system shown in Fig. 4, whose refractive index change in the vertical plane is + 13- + 10.5 dpt is used to correct aphakia.

Example 12

The continuously varying refractive power of the ophthalmic optical system shown in Fig. 4 in the vertical plane is +13 to +10.8 dpt and is used to correct aphachia.

The radius of curvature of the fracture surface of the front optic lens The radius of curvature of the rear optic lens 40 is the radius of curvature of the front optical surface of the second optical lens 45 is the radius of curvature of the second optical lens distance along the optical axis refractive index refractive index on the axis (d ' _c = 3.5; 4 ^Γ = 3.5)

R1 = 22.0 mm

R ₂ = 27.0 mm

_R3 = 22.0 mm

R ₄ = 27.0 mm d = 3.5 + 0.5 mm

0.5 mm

1 D - 1.6126 + 13 dpt = 80 °

The front and rear refractive surfaces of each optical lens are spherical.

It should be noted that in Examples 10, 11 and 12, the posterior refractive surface 65 of the second optical lens, which can be described by a quadratic equation, has zero or near zero eccentricity or torus surface to correct ocular astigma.

The goodness-of-image correction performed with the ophthalmic optical system described in Example 10 (used to correct aphakia)

Refer to Tables 1, 2, 3, and 4, and Diagrams 5, 6, 7, 8, and 9 for further explanation.

For better clarity, differences in the ophthalmic optical system are taken into account when calculating radius refraction.

Table 1 shows the values of deviations of the ophthalmic optical system for an object located on the axis of the optical system. Table 1 has the following designations:

h - height of the ray at the entrance pupil;

ΔS ′ values show spherical longitudinal deviations of the posterior focal plane of the ophthalmic optic system;

og ′ values represent transverse transverse deviations of the posterior focal plane of the ophthalmic optic system;

η - values represent deviation from sinus law;

W - spherical wave misalignment; tan u 'values represent the value of the aperture angle in the image space.

As shown in Table I, up to a 3 mm value of the entrance pupil of the ophthalmic optical system 15, the longitudinal deviation of the spherical ΔS 'is not greater than -0.293 mm and the transverse deviation of the spherical Sg' is -0.0044 mm.

Table 1

Point of axis

h DIG 5g ' W tan u ' 1.50 -0.293 -0.0044 -0.096 -0.104 0,024 1.30 -0.220 -0.0029 -0.064 -0.0046 0.019 1.06 -0.147 -0.0016 -0.032 -0.012 0,014 0.75 -0.073 -0.0006 -0.020 -0.005 0.011 0 0

Table 2 illustrates the deviation values of the ophthalmic optical system with respect to an object outside the optical axis passing through the optical system. In Table 2:

β - angle of view;

tan 0 '- tangent to the value of the angle of view in the image space;

y '- image size of the posterior focal plane of the ophthalmic optical system;

Xt - value of vertical deflection;

X $ - value of the image inclination in the saggital plane;

⁴⁰ S _E in - entrance pupil of the system distance measured to the rear surface Saus - ^the system exit pupil distance based on the front surface;

Á% - Distortion in%.

Table 2 shows that the value of astigmia at position S _e j _n = -14 mm is not more than 3 dpt for Xg-XJ.

Table 2 Off-axis point

0 tan 0 ' y ' xt ^X S. Sein Saus THE% - 80 ° -1.540 162.68 . -3'4,49 -36.55 -14.0 -9.10 -60.27 -669 ° -1.139 120.38 -21.14 -25.24 -14.0 -9.15 -36.92 - 56 ° -0.894 86.60 -10.80 -15.43 -14.0 -9.20 -20.78 - 40 ° -9.523 55.13 - 3.88 - 7.08 -14.0 -9.27 - 8.98 -14.0 -9.35

-919

Table 3 illustrates the deviation values of the ophthalmic optical system for an object located outside the optical axis of the system in the case of an oblique beam passing through the orthogonal section of the system. The table shows the 5 different values of the angle of view 0 as a function of the size of the m pupil entering the system and the values of the spherical transverse deviation in the perpendicular plane. As shown in the table, the spherical cross-sectional deviation is limited to a maximum of 0.2 mm with respect to the maximum viewing angle 0.

Table 3

Vertical engraving

0 = -80 ° 0-69 ° 0 = -36 ° 0 = -40 ° m Ay ' m y'A m Ay ' m Ay ' 1 2 3 4 5 6 7 8 -147.56 -0.200 -109.25 -0.206 -78.59 -0.155 -49.80 -0.090 -147.64 -0.172 -109.37 -0.175 -73.75 -0.130 -49.97 -0.073 -147.73 -0.140 -109.51 -0.140 -73.93 -0.102 -50.18 -0.055 -147.85 -0.098 -109.69 -0.096 -79.16 -0.068 -50.46 -0.035 -148.12 0 -110.12 0 -79.70 0 -51.11 0 -148.40 0.093 -110.54 0.083 -80.24 0.049 -51.75 0,016 -148.51 0,130 - 110.71 0.114 -80.45 0,064 -52.01 0,017 -148.55 0,157 -110.84 0.136 -80.62 0.073 -52.21 0,017 -148.67 0,180 -110.95 0.154 -80.76 0,080 -52.38 0,015

Table 4 illustrates the deviation data of the ophthalmic optical system for an object located outside the optical axis of the system at an oblique beam passing through the sagittal section of the system. In Table 4:

M - size of incoming pupil in sagittal section with oblique beams;

the δ5 'value represents a spherical transverse deviation of the ophthalmic optical system in the sagittal section;

óg '- the system coma.

Table 4 shows that the spherical deviation at maximum viewing angle is not more than -0.6 mm.

Figure 5 illustrates curve "A", which plots the height of the entrance pupil of the ophthalmic optic system as a function of the spherical longitudinal deviation of that system for an object located on the optical axis of the ophthalmic optic system. The values of R on the ordinate are the size of the entry pupil in mm, and the values on the abscissa are the values of ΔS ', which give the values of the spherical longitudinal deviation in mm.

The curve "A" shows that as the pupil h increases, the longitudinal deviation of the spherical AS 'increases continuously and the spherical longitudinal deviation at the periphery of the pupil (h - h) is -0.2 mm.

Fig. 6 is a graph showing curve "B", illustrating an image deflection relative to a vertical plane as a function of the ophthalmic optic system and curve "C" a sagittal plane as a function of the viewing angle. On the ordinate, the 0-value of 40 is two (angle of view, in degrees), and the abscissa is X (and Xs) (values of image deflection relative to the vertical and sagittal planes, respectively).

If you look at the curves "B" and "C", you can see that as the angle 0 increases, the image deflection increases continuously in the vertical and sagittal planes. From the diagrams, it can be seen that in the ophthalmic optical system of the present invention, the astigma 50 is of negligible value (X (- XJ)), which is necessary for the monitoring devices.

Curve D in Fig. 7 illustrates a spherical transverse deviation of the ophthalmic optic system as a function of the size of the exit pupil at a maximum angle of 0, i.e., 0 = 80. On the ordinate, the Ay 'values (spherical transverse deviation in mm) and the abscissa were set to Atan 0' = = tan Br - tan Skin, with 60 tan Bk tangent to the radius of the outgoing pupil rim. and tan Lo is the tangent to the exit angle of the beam passing through the center of the exit pupil.

The Atan B 'value is the size of the 65 outgoing pupils of the ophthalmic optic system.

-1 021

Table 4 Saggital section

<< O -0.112 ΧΟ 8 ο I 00 c θ ' 1 • r 8 a 1 She She She IC She Λ τΓ | bO 02 Φ She 8 Q II "Ο cT ο * She θ ' o. 1 ox 1 ο 1 She i "-4 <p t-Η a-4 S f · ^ She IC 1 IC 1 c * 1 IC ο SHE cm 1-1 Γ- CM (N CN r-f t-1 She 40 θ ' 1 θ ' 1 θ ' 1 SHE She xo r- οο 00 8 <C cc CM r-1 | Oo She φ She She She yl 40 cT οΓ cT θ ' 1 Γ- 1 οο ! αχ She χο χ © χο _λ Γ- s σΓ σΓ > 0 cC She Γ- 1 Γ- 1 r- 1 t 1 CC CM 8 IC OX 40 Tf ο " 1 CC Φ 1 CM Φ 1 CM o She She ox '- ( XC IC XO I eo 06 3 CO o She Q II 40 ο θ ' SHE She <Ώ. 1 Γ- 1 8 She ο ^ -4 s ο ο She She She 1 * - < 1 1 cc cc <c V) IC CM □ rj φ IC CC She <p ο 1 C 1 θ ' She ° p αχ She IC 00 αχ Γ- uc CM | Oo ο She She She II 40 ο θ ' cT cT <Ώ. 1 8 1 8 1 8 She s 00 00 tt oo © Τ * "4 1 1- ( 1 7 7

-1 123

If you look at the "D" curve, where β = 80 °, it can be seen that the ophthalmic optic system is coma-free and that the spherical transverse deviation in the entire pupil region is insignificant.

"E" curve of Figure 8 the system of a spherical ^five transverse deviation küépő dependence illustrated in pupil size as a function of β - 40 ° viewing angle. The ordinate A ' _y ' (spherical transverse deviation in mm) and its abscissa B '= tan Br - tan BJ> were applied to you in ¹⁰ increments where tan Bk is the tangent to the exit angle of the ray passing at the exit pupil edge , while tan B0 is the tangent to the exit angle of the beam passing through the center of the exit pupil. ¹⁵

Figure 9 illustrates a "F" curve showing the magnitude of the output pupil as a function of the transverse spherical deviation of the ophthalmic optic system when the β-angle of view is zero. The ordinate axis has an Ay 'of 20 (illustrates the spherical transverse deviation in scale) and the tan B' of the abscissa; tan B '= tan tan Returns a large value.

When looking at the curves "E" and "F", it appears that the spherical transverse deviation is small 25 and that the ophthalmic optical system is coma-free.

Figures 10, 11 and 12 illustrate a frame for an ophthalmic optical system according to the invention. The frame has frame edges 20 (see Fig. 10) consisting of 30 segments of two segments 21 and 22 (see Fig. 11). The segment 21 is provided with a thin rim of the ophthalmic lens and a segment 22 with a thick rim of the ophthalmic lens. The frame edges are made of a flexible material, e.g. are made of copper. On the frame edges 20 are fastened stems 23 (see Fig. 12. 35). The nose saddle 24 connects the frame edges 20, is curved in the opposite direction to the legs 23, and is located at the required maximum viewing angle of 30 ° (see Figure 11). To properly align the ophthalmic lens to the face of the wearer 40, the nose saddle 24 is inclined at an angle from the plane of the face which is the angle between the face of the wearer and the circumference of the nose. 45

This cross-section described above is mainly used to accommodate negative ophthalmic systems.

13, 14 and 15 are the framework for ocular optical system ⁵⁰ is illustrated filled with examples of several possible pane subdivision. The frame has a frame rim 25 (see FIG. 13) formed by segments 26, 27 and 28, 29. A thin rim of the ophthalmic lens is inserted into the segment 26 and the bracket 30 (see FIG. 14) is secured to the rim 25. The nose saddle 31 connects the frame edges 25, is bent in the opposite direction to the brace, and is arranged at an angle to the required viewing angle of the person wearing the glasses (see Figure 15). This frame construction is used mainly for attaching 60 positive ophthalmic optical lenses.

Figures 16, 17 and 18 show a frame for ophthalmic optical systems consisting of two optical lenses.

The frame has two 32 frame edges (see fig

16) which are segment-shaped. The height of segment h is greater than the inner radius R _{5 of} the frame rim 32. The inner surface of the segmented frame flange 32 has two grooves 33 (see FIG

17). Thin-rim ophthalmic lenses are inserted into the grooves 33. Between the grooves 33 there are grooves 34 (see Figures 16, 17) starting from a plane extending above the segment envelope. On the frame edges 32 are fastened stems 35 (see Fig. 18).

The nose saddle 36 connects the frame edges 32 and is bent in the opposite direction to the stems 35 and is positioned with respect to the required viewing angle of the person wearing the glasses (see Figure 17). In order to properly adjust the ophthalmic optical system to the face of the person wearing the glasses, the nose saddle 36 is inclined at a p-angle to the face plane. This angle represents the angle between the plane of the face of the person wearing the glasses and the mantle of the nose saddle.

This frame construction is preferably used for ophthalmic optical systems for aphakic correction.

The method for determining the refraction of an optical lens is illustrated in Figures 19 and 20. The apparatus shown in Figure 19 shows a method of measuring the refraction of a portion of an optical lens, which is used to view an object that has the best visual acuity, e.g. He is at a distance of 250 mm. The apparatus illustrated in FIG. 20 is used to determine the refraction of the portion of the optical lens used to view objects that are in infinity.

The apparatus consists of a telescope 37 (see Figures 19 and 20) having an objective lens with a .38 Fob rear focal point and is provided with a magnifying glass 39, which has a focal point F _O k. In the focal plane of the magnifying lens 39 of the telescope 37, a crosshair 40 is disposed. The telescope 37 has 41 entry pupils and 42 exit pupils.

The optical lens 43 to be measured is positioned in front of the entry pupil 41 of the telescope 37.

The object 44 is located at a distance of 250 mm (see Figure 19) or infinity (see Figure 20) in front of the front surface of the optical lens 43 to be measured. The calibration lens 45 is located between the optical lens 43 to be measured and the entry pupil of the telescope 37.

The essence of the method for measuring the refractive value of an optical lens is to focus the telescope 37 (see FIG. 19) on the object 44 by aligning the objective lens 38 and overlapping the arc of the object 44 with a signal located in the plane of the the magnifying lens 39 is at the front focal point. The object 44 is 250 mm from the front surface of the optical lens 43 to be measured.

The center of rotation of the optical lens 43 to be measured is then aligned with the center of the entry pupil 41 of the telescope 37, and the optical lens 43 to be measured is rotated 65 until the rotation is at that distance.

Corresponds to -1225, at which distance the telescope 37 is focused.

By compensating with the calibration lens 45, the refractive power φ of the optical lens 43 to be measured is measured. At the moment of measurement, the object 44 is sharply imaged on the cross-member 40 ^{5 of} the telescope 37.

The rear apex R of the lens differs from the refractive power of the lens by K.

R = K (1) where

Φ - refractive index of the lens - refractive index of the lens ri - radius of the frontal fracture, ^{13 * 15} where

K = --------- 1 - ^npl . d ²⁰ ii

44 refraction for infinity object in the measurement of (see Figure 20) of the optical lens to be measured 43 is rotated until its area which corresponds to the spacing of concentrated Tar- ²⁵ which is focused by the telescope 37.

In measuring the Φ-refractive power of the optical lens 43, compensation with the calibration lens 45 is performed until a sharp image of the object 44 is displayed on the reticle 40 of the telescope 37. With the above formula, the refraction value of the lens is determined.

According to said method, the refraction of an object can be measured at any distance between infinity and 250 mm. Meanwhile, the telescope 37 is focused on the object. The optical lens to be measured is rotated from the entry pupil of the telescope to the region ⁴⁰ needed to observe the object at this distance.

Example 13 ⁴⁵

The following lenses for presbyopia correction are used as measurable lenses:

the frontal fracture 50 radius of curvature R1 = 22.0 mm the rear breaking surface radius of curvature R ₂ = 22.0 mm the thickness of the lens- is constantly changing 55 section d = 0.5-5.0 mm the refractive index = 1.6126 the thin lens flange breaking strength 0.2 dpt the thicker lens flange 60 breaking strength 2.7 dpt the thin lens flange refraction 0.2 dpt the thicker lens flange refraction 2.96 dpt 65

Example 14 The following lenses for hypermetropia and presbyopia correction are examined: / the frontal fracture radius of curvature . R1 = 22.0 mm the rear breaking surface radius of curvature R ₂ = 25.0 mm the thickness of the lens infinitely variable range of d = 0.5-5.0 mm the refractive index 17 _d = 1.6568 the thin lens flange breaking strength 3.8 dpt the thin lens flange value of refraction 3.8 dpt the thick lens flange value of refraction 7.1 dpt

Example 15

The optical lens used for correction of myopia and presbyopia is as follows:

the radius of curvature of the front crushing surface is the radius of curvature of the rear crushing surface R = 22.0 mm _R2 = 20.0 mm the thickness of the lens- is constantly changing range of d = 0.5 + 6.0 mm the refractive index = 1.6126 the thin lens flange breaking strength —2.5 dpt the thick lens flange breaking strength 0.4 dpt the thin lens flange value of refraction -2.5 dpt the thick lens flange value of refraction 0.45 dpt. \

It will be apparent to those skilled in the art from the foregoing embodiments of the invention that all of these objects have been accomplished. Our actions are included in the claims. However, it is also to be understood that minor changes to the ophthalmic optic system, frame, and refraction measurement process can be accomplished within the scope of the invention, but that the scope of such changes is within the scope of the claims.

The ophthalmic optical system described in detail above, whose dioptric number varies continuously in the vertical plane, is suitable for viewing both distant and near objects.

The disadvantage of the known multi-focal spectacle lenses is that they are extremely expensive to produce and cause significant image distortion.

The ophthalmic optical system of the present invention is indicated for continuous wear and does not cause fatigue. Cost of producing Glasses a

-1327 is only slightly higher than the cost of producing standard lenses for short-range or far-sight correction. Preferably, the goggles of the present invention have a wider viewing angle (to 80 °) and it is further mentioned that image distortion does not occur.

The method of the present invention makes it possible to measure the refraction of an object at a required distance in any lens region.

Patent claims:

Claims (7)

Patent claims: An ophthalmic optical system having a continuously varying refractive power in the vertical plane, the optical lens having anterior and posterior refractive surfaces, the latter of which is described by a quadratic equation, characterized in that the anterior fracture surface (2) is formed spherically and arranged relative to the rear refractive surface (3) such that the thickness of the optical lens (1) decreases from the lower edge to the upper edge and that the focal length of the ophthalmic optical lens gradually changes in the vertical plane to the max. Within 3 ranges up to 25 dioptres. An embodiment of an ophthalmic optical system according to claim 1, characterized in that it comprises an additional optical lens (16) formed in the same way as the first optical lens and that both optical lenses (13, 16) arranged so that their optical axes overlap and each optical lens (13, 16) has the same sign of refractive power in the same section. 35 3. An ophthalmic optical system according to claim 1, characterized in that, for correction of presbyopia and hypermetropia, the optical axis runs in the middle of the sagittal section of the optical lens (5) and is located near the lower thick edge 40 of the optical lens (5). . An ophthalmic optical system according to claim 1, characterized in that, for correction of presbyopia and myopia, the optical axis runs in the center of the sagittal section of the optical lens (9) and is located near the upper edge of the optical lens (9) up to 5 mm thick. a. An embodiment of the ophthalmic optical system according to claim 2, characterized in that, for correction of presbyopia and aphakia, the optical axis runs in the middle of the sagittal sections of the optical lenses (13, 16) and the lower maximum of the lenses (13, 16) is 5 mm thick. are located near the rim. Frame for an ophthalmic optical system according to claim 1, having optical lens mounting flanges which are interconnected by a nasal saddle and having stems fixed to the frame parts, characterized in that the frame flanges (20) are made of at least two segments. (21, 22) and that one of the segments (21, 22) serves to hold the thin rim of the optical lens, and that the nose saddle (24) is inclined in the opposite direction to the stems (23) and that a maximum of 30 ° is required. is based on the value. A method for measuring the refractive value of an ophthalmic lens according to claim 1 by focusing a telescope on the object, inserting the optical lens to be measured between the telescope and the object, then rotating the optical lens to be measured about a pivot point and refraction of the lens. for measuring the refractive power of the lens, characterized in that after inserting the optical lens (43) to be measured between the telescope (37) and the object (44), the center of the entry pupil of the telescope (37) obscures the pivot of the optical lens (43) and rotating the optical lens (43) to be measured to a thickness dimension corresponding to the distance between the front surface of the lens and the object (44), and then compensating the refractive power of the optical lens (43) to compensate. ) until then gauze until the object (44), a sharp image of the telescope (37) magnifying lens gyújtósflcjában (39) appears. Figure 5 Figure 20 Responsible for publishing: Director of Economic and Legal Publishing 84,4455 - Zrínyi Printing House, Budapest