UA122709C2 - METHOD OF SYNCHRONOUS RATRAYSING MEASUREMENT OF REFRACTION ERRORS OF THE EYE AND REFRACTION INHOMOGENEITY OF ITS CRYSTAL - Google Patents

Abstract

The invention relates to the field of medical ophthalmic instrumentation. The method is used to measure the refraction and refractive errors of the optical system of the eye, including the diagnosis of the degree of lens dysfunction due to the degradation of the homogeneity of its refractive characteristics. The eye is probed point by point of the input aperture with a central and at least one lateral or several, for example two or four, lateral thin laser beams so that each side beam intersects the central beam at the point of entry of the latter into the eye. The location of the projections of the laser beams on the retina is reflected on a photodetector using an optical system focused on the retina. Measure the coordinates on the retina of the projections of all rays. The refractive errors of the optical system of the eye as a whole are calculated from the coordinates of the eye and the coordinates of the projections of the central beam on the retina, and the pairwise difference of coordinates between the position of the projection of the central beam and each side beam for each probing point is used to calculate refractive inhomogeneity. The invention provides a measurement of the spatial heterogeneity of the refractive characteristics of the lens in a direct indirect manner.

Description

provides measurement of the spatial heterogeneity of the refractive characteristics of the lens in a direct, unmediated way. that their eat5

OO : ; to me

KE kovi still p r Eh 4 Be M so Kok MV me p py shin en pojezhentnnnny ft nkhhu ih U. within the limits of or KOJZ jo ze. ! - «KE --4 Kok U pet ter suultlgtiltxh A z A nn pov M m) Sashi fen nie ni vh chi i na

Fig. 2

The invention belongs to the field of medical ophthalmic instrumentation, in particular, with the purpose of ophthalmological examination, measurement of refraction and refractive errors of the optical system of the eye as a whole for the purpose of surgical or non-surgical vision correction, as well as diagnosing the degree of dysfunction of the lens caused by the degradation of the homogeneity of its refractive characteristics, with for the purpose of its timely replacement.

Technical level

Measurement of refractive errors of the eye and its components is an important diagnostic task of refractive and cataract surgery.

One of the well-known methods of measuring refractive errors of the eye is based on the application of the Hartmann-Sheck sensor (9. Giapueyi a. Te Oriisa!| bosieiu oi Ategisa, 1994, Moi. 11, Mo. 7, 1949-1957). According to this method, a thin laser beam is directed to the retina, combining it, as a rule, with the visual axis of the eye, the image of the projection of the laser beam onto the retina is displayed using a matrix of microlenses on the photosensitive surface of the video camera. From the received data, a wavefront error map and/or a refractive error map are reconstructed (usually a wavefront error map is called a wavefront map, and a refractive error map is called a refraction map to shorten the term).

Among clinical aberrometers, the principle of simultaneous projection of a regular structure of light onto the retina proposed by Cherning is also used. Its laser modification is described in the work of R. Miegaye! etc. Osciag oriisa! aregoteieg og siipisa! is. Washigpai oi Vioteadisa! Oriisv, 2001, Moi. 6, Mo. 2, pp. 200-204. A collimated laser beam illuminates an opaque screen with holes, forming a system of light spots on the retina. According to the structure of these spots, the aberrations of the wave front are calculated.

In clinical practice, the ray-tracing, consistent in time approach has found wide application (V.V. Molebnyi et al. Eye aberration refraction meter. Patent of Ukraine 46833,

Bulletin Mo 6, 17.06.2002, and its mirror - US patent 6932475), by which the eye is probed with a thin laser beam sequentially in time point by point of the input aperture of the eye, display on the photodetector the location of the laser beam projections using an optical system focused on the retina, measure the spatial positions of these images

The refraction of the optical system of the eye at a given point is calculated from the projections calculated into the plane of the retina, based on the coordinates of the entry into the eye and the coordinates of the projections on the retina, and based on the refraction values at each point, the surface of the wavefront is reproduced in the form of spatial functions by approximating them using, for example, of Zernike polynomials (9. M. Uapd apa 0. E. 5iima, Uame-igopi ipiegrgeiaiop m/yp 2etike roiiupotia!5. Arriiv Oriisv, 1980, Moi. 19, r. 1510-1518) or splines (S. V. Molebny etc. The method of measuring wave aberrations of the eye.

Patent of Ukraine 67870, Bul. Mo 7, 15.07.2004). The reproduced spatial function is presented in the form of a refraction map. Based on the results of the measurements, a number of other parameters are also calculated.

Other methods of measuring the wave front are also known. Their detailed analysis is given in the work of M. MoiIerpu, UUameytopi zepzoiv5, SNariviegi 2 ip She rooK Napabrook oi Mizza! Oriisv, R. Apai,

E9., Moishte 2, years 17-36, SVO Rgezz/TGauyog 4. Egapsiz, Vosa Nayup-Y opdop-Mem/ Moik, 2017.

It is possible to obtain information about the refractive characteristics of the lens, if the characteristics of the wave front of the optical system of the eye as a whole and the characteristics of the wave front of the cornea are known. Following this path, the topography of the cornea is measured, based on the topography of the cornea, the wavefront error map is reconstructed, the path difference at the corresponding points of the input aperture between the values for the wavefront of the optical system of the eye as a whole and the values for the wavefront of the cornea is determined as the value of the wavefront of the lens. Methods of measuring the topography of the cornea are widely known and described in the patent literature in numerous modifications. Usually, they are based on the analysis of the projection of a regular light structure on the cornea, thanks to which the topography of the corneal surface is reconstructed.

An overview of these methods from the point of view of clinical application is given in the book Sogtpea! Torodgarnu ip Te U/ameitopi Ega, M. UMMapo, Ea., ziask Ips., Tnogoiage, M. U., 2006.

Since the measurement of the errors of the wavefront of the eye as a whole and the errors created by the cornea are performed by devices that work on different principles, the problem is the need to align their coordinate systems. They are trying to overcome the shortcoming by placing both devices on a common base and even aligning their optical axes. However, with the use of non-identical principles of centering, this drawback does not disappear. It was proposed to use the same laser beams to measure the topography of the cornea as for measuring the refractive characteristics of the eye as a whole (M. MoiIerpu, ei aYi., Memtoa apa demise og 60 vupspgopoi5 tarripa oi She yi0ia!| geigasiop pop-potodepeyu oi She euye apa ate geigasiime sotropepiv. 05 Raiepi 6409345, supplement 22, 2002). The rays reflected from the cornea are projected onto a separate screen and the position of the reflected laser rays on the screen is analyzed. The necessary mathematical apparatus for such an analysis was developed (M. MoiIerpu apa U. BoKytepko.

Ratrea Ieazi-zapage5 arrgoasni og roipi-z0shgse sotveai Yuyuroagarnu. OrniNa!tis apa RNuzioiodisa!

Oriisv, 2009, Moi. 29, pp. 330-337), which made it possible to significantly increase the accuracy of combining both measurements.

However, in the case of complex topography of the cornea, for example in the case of keratoconus, a measurement based on an indirect calculation of the refractive characteristics of the lens by subtracting the wave errors of the cornea from the wave errors measured for the eye as a whole may lead to incorrect results, meaning that these wave errors are pre-smoothed during approximation, that is, they can lose the most valuable information from the point of view of the degree of degradation of the lens - the high-frequency (spatial) component of the refractive inhomogeneity of the lens.

The given arguments indicate the need to measure the spatial heterogeneity of the refractive characteristics of the lens in a direct, unmediated way, which is the task of the invention.

The task is solved in this invention by probing the eye point by point of the entrance aperture with the central and at the same time at least one side or several, for example two or four, side thin laser beams so that each side beam crosses the central beam at the point of entry of the latter into the eye. To simplify the calculations, it is advisable to arrange the side beams in orthogonal planes. The location of laser beam projections on the retina is displayed on the photodetector using an optical system focused on the retina. They measure the coordinates on the retina of the projections of all rays. According to the coordinates of the entry into the eye and the coordinates of the projections of the central beam on the retina, the refractive errors of the optical system of the eye as a whole are calculated and displayed, for example, in the form of a map, and the pairwise difference of coordinates between the position of the projection of the central beam and each of the side beams for each probing point is used to calculate the refractive inhomogeneity of the lens.

Since all rays pass through the same point of the entrance aperture, they are in the same direction

They gradually change their inclination after passing through the cornea, but through the lens they take different routes. On the retina, their projections will be at some distance in the x and y directions from the projection of the central beam. The disparity of these distances for different probing points is a consequence of the refractive inhomogeneity of the lens. Therefore, this inequality is a characteristic of the refractive quality of the lens.

Fig. 1 shows an example of the course of rays in the eye, and one of the rays is central, and the other is lateral.

Fig. 2 shows an example of the structure of the device, which, using a diffraction grating, creates a system of rays consisting of central and side rays when probing the central point of the entrance aperture of the eye.

Fig. C is the same example as in fig. 2 when probing the peripheral (upper) point of the entrance aperture of the eye.

Fig. 4 is still the same example as in fig. 2 when probing the peripheral (lower) point of the entrance aperture of the eye.

Fig. 5 depicts the path of rays in the receiving channel and an example of the location of the images of the ray projections for the case of use in probing the zero and first orders of diffraction in orthogonal directions.

Fig. 6 shows an example of a signal from the output of a line of photodetectors in one of the orthogonal directions when probing with the central and two side beams.

Fig. 7 is similar to fig. b illustrates the signal from the output of the line of photodetectors in one of the orthogonal directions when probing with a central and one side beam.

In fig. 8 shows a photograph of a lens with a lenticonus (Alport's disease - AIProgt5 disease), taken with the help of a slit lamp.

Fig. 9 illustrates the location of the sequence of points of entry of rays into the eye (point trajectory).

In fig. 10 shows the time-expanded trajectory of the projections on the retina of the central and one side rays - retinal point diagram (heyipa! zroi aiadagat) with sweep in chavba.

Fig. 11 represents the wavefront error function along the y-axis introduced by the lens, calculated from the sequence of measurements illustrated in Figures 9 and 10.

In fig. 12 shows the network of points of entry of rays into the eye, necessary for the calculation and construction of the two-dimensional distribution (map) of refractive errors and wavefront errors.

Fig. 13 illustrates the result of measuring the wavefront errors (as a color-coded error map) produced by the lenticonus lens shown in FIG. 8.

Information that confirms the possibility of implementing the invention

The method of synchronous raytracing measurement of refractive errors of the eye and refractive inhomogeneity of its lens is described below with references to the drawing figures.

In fig. 1 central ray 1 is directed into the eye parallel to the visual axis SoMo and enters it at point Si. For simplicity, the thickness of the cornea will not be taken into account. The further path of ray 1 will pass through points Ia (apiegioi, front surface of the lens), I p (rosietiog, back surface of the lens), B: (surface of the retina).

Side ray 2 is directed at an angle to the central ray at point C. After crossing the cornea, it will be inclined relative to the central ray at an angle r. Its further path will pass through points I ha, Igr, B"- In fig. 1 shows a case of hyperopic error.

The distance Х of the point МН: from the point Но, i.e. from the point of intersection of the retina with the visual axis corresponds to the total ametropia of the eye at the given point C: the entrance aperture of the eye on the route С.-И 1а-Й 1р-Ві

The distance bh of point P" from point B: is determined by the angle of inclination and and the total ametropia of the eye along the route Si-I 2a-I zr-B2. Under the condition that the refractive parameters are identical on the C-Yia and C-II2a sections of the tracks, as well as on the Ir-B:i and Igr-H2 sections, the distance bh can change for different points C of the rays entering the eye only if the refractive parameters of the lens (with unchanged accommodation) differ on the sections of the tracks Ha-I r and | (tsa - | (r.

Thus, bh carries information not only about the angle and inclination of beam 2 relative to beam 1, and as a result, the deviation of its projection on the retina relative to the projection of beam 2, but also information about how much this deviation differs from the calculated one, where we consider calculated deviation in the assumption that the refractive parameters of the lens on the routes I a-I r and Tsina - inr are the same. The difference between the measured value and its calculated value is a measure of the inhomogeneity of the lens, which can be converted into a refractive error and/or an error of the wavefront introduced by the lens.

An example of the structure of the device that creates a system of beams, which consists of central and side beams, is shown in fig. 2. The device consists of a sequentially installed laser, a scanner, a Lee collimation lens, a DG diffraction grating and a Badal projection telescope with two positive lenses Lo and Lz. The equivalent scanning center Ox must coincide with the front focus P: of the Lee collimating lens. The laser can emit both in the visible part of the spectrum and in the near infrared. Invisible infrared radiation is preferred for patient comfort. But at the same time, do not forget to recalculate the parameters in the visible range. As for the scanner, for clinical practice, a fast-acting acousto-optic deflector is used with a speed of changing the beam from one point of the eye aperture to another, which is units of microseconds. But other constructive options are also possible, their analysis and selection go beyond the scope of this invention.

The diffraction grating installed after the collimation lens should be located in the front focal plane of the first lens L" of the Badal telescope (the front focus Eg2 coincides with the exit point Oa from the grating). The back focus E" of this lens and the front focus Ez of the second lens Lz of the telescope

Badalya should match. One of the lenses of the Badal telescope can perform the function of compensating for the general ametropia of the eye, but since this is beyond the scope of the present invention, we do not consider this function here. The entrance aperture of the eye must be located in the back focal plane of the lens Lz (the point of entry into the eye Oo coincides with the back focus z). Fig. 2 illustrates probing of the central zone of the aperture (at the point Oo, which, for example, coincides with the point of intersection of the cornea with the visual axis). Probing the peripheral points of the entrance aperture of the eye using the structure shown in fig. 2, illustrated in fig. Z - at the upper point Oo", in fig. 4 - at the bottom point Oo".

The laser beam from the laser output is fed to the scanner, which performs an angular scan, the collimating lens converts the angular scan into a scan ("permutation") of the laser beam parallel to itself to enter the eye parallel to the visual axis. After passing through the diffraction grating, the laser beam is "multiplied" and consists of a zero-order beam that goes straight without changing the primary direction and beams of the first and higher orders, inclined to the zero-order beam. From this set, you can select (choose) zero (central) and one or more lateral ones. The grid can be one-dimensional or two-dimensional. With a two-dimensional lattice, it is possible to select rays of zero and first orders in orthogonal directions. For the principle of operation of this 60 method, it does not matter how many side rays are selected. This will affect only mathematical relationships when processing the received data. Figures 2, 3, and 4 show a one-dimensional lattice, from the output of which rays of zero Po and both first orders P.i, P.i are selected. The exit points Os, Os", Od" of the Po, Po: and P-th ray system from the grating are conjugate to the points of entry into the eye Oso, OoOo" for each ray entering the eye. The further paths of the rays in the eye are similar to the paths illustrated by the figure 1.

Reception of signals from the eye is carried out using a photodetector schematically shown in fig. 5. In the return course of radiation from the eye, the second lens Lz of the Badal projection telescope is used as the first lens of the Badal receiving telescope. Between the first Lz and the second La lenses of this telescope, a mirror with a polarizing coating is installed, which reflects the orthogonally polarized component in the direction of the second Li lens, to eliminate reflections from the return signal. The photodetector lens is installed after the Lee lens. so that the planes of the retina and the photodetector are conjugate, i.e., the points NK, Ko, and HB in the plane of the photodetector are images of the points В.і, Во, and В. in the plane of the retina. Their position in the plane of the photodetector is determined by the course of the main rays of the GP-i, GPo and GP, passing through the nodal point M of the eye.

On the tab fig. 5 shows an example of images of the projections of five rays: the zero-order ray No, the first-order rays HB, Ah. along the x-axis and rays of the first order of VU,

VU along the y axis. The position of the Ko image carries information about the general ametropia of the eye at the given point of entry of the rays into the eye, and the position of the VU-1st, VH images. carry information about the deviation of refraction in the lens on the adjacent paths in the plane with the x axis. Similarly, the positions of the VU and TU images carry information about the deviation of the refraction in the lens on the adjacent tracks in the plane with the y axis. The position of all these images is measured as the position of their centroids when using a matrix photodetector.

When using detector lines, the optical system is designed to obtain two projections: on the x-axis and on the y-axis. In this case, the position of the maximum of the distribution of the signal level along the corresponding axis is measured (in other words, the number of the line element from which the signal is maximum is determined). Since, from the point of view of this method, it is not fundamental how the photodetector is designed, we will consider the appearance of the signals for the design with projections on orthogonal axes, while we will consider one of the axes (x or y) as an illustration.

In fig. b shows the signal read from a line of detectors (for example, Natataiza type 54114) in one of the orthogonal directions when probing with the central and two side beams. For simplicity, the signal is shown normalized both by amplitude (the amplitude of the image of the projection of the central beam is taken as one) and by location on the coordinate axis (that is, the total ametropia of the eye at this point is not taken into account - the maximum of the signal is at the center of the coordinates). The distance b.1 between the projections of the central beam and the side beam (plus the first order of diffraction) determines the slope of the normal to the wave front in the plane of the slope of the side beams. Similarly, the distance b between the central and side beam projections (minus the first order of diffraction) determines the slope of the wave front in the opposite direction. To determine the inclination of the wavefront in the orthogonal direction, it is necessary to add the side beam/beams inclined in the orthogonal plane.

Fig. 7 is similar to fig. b illustrates the signal from the output of the line of photodetectors in one of the orthogonal directions when probing with a central and one side beam.

Several options for processing and presentation of processing results can be offered.

Refractive errors of the eye are usually represented in the form of a map, where refractive errors are presented as scalar values in the form of a two- or three-dimensional image with color coding of the error value. Taking into account the vector nature of the error can include an additional map, for example, a map of the directions of maximum slopes.

As for the refractive errors of the lens, it is advisable to present the results in the form of a gradient map, which can be scalar or with the addition of a map of normals to the surface.

The algorithm for its calculation can be as follows:

The optical power of the eye at a given point is calculated by the value dDx (Fig. 1);

The estimated value of b5 xr is calculated;

The difference between the calculated bhr and the measured value of bhr is calculated, i.e. (bОхр - Ох);

The refraction gradient Аг at a given point in the direction of the lateral beam inclination is calculated from the value (бхр - бх). If there are two or four side rays, then the orientation of the normal to the error of the wavefront for this probing point is calculated.

An example of measuring the refractive errors of the lens will be demonstrated on the example of a lens with a lenticonus (Alport's disease - AIProgi5 aizeease), the image of which is made with the help of a slit lamp and is presented in fig. 8. The lenticonus is located on the outer bo (apietiog) side of the lens (on the left in the photo) and is a local bulge in the central zone of the lens. The study of its refractive inhomogeneity can be performed along some trajectory, for example, in a vertical section along the y axis (Fig. 9). As in fig. 1, point

So corresponds to the intersection of the cornea with the visual axis. At each point of the trajectory C); the central and, in the simplest version, one side beam are directed into the eye. It is advisable to place the side beam in the plane that coincides with the scanning direction.

Fig. 10 illustrates the nature of the change in the relative position of the projections of both rays when changing the coordinates of the rays entering the eye. The vertical axis corresponds to the position of the probing point at successive points in time, point by point along the y-axis. The horizontal axis corresponds to the value of the deviation of the projections of the first (central) Vu) and second (side) B(2") and rays from the "zero" position along the y axis, i.e. from the point Ko of the intersection of the retina with the visual axis. At the same time, D; is a value that determines the refractive error of the eye as a whole, and b; - the refractive error of the lens. Note: to simplify the explanation of the principle of operation, variations along the x-axis are not considered. The graph of wavefront errors along the y axis is shown in Fig. 11.

A map of refractive errors or wavefront errors of the lens can be obtained by probing across the entire entrance aperture of the eye. An example of the distribution of probing points is shown in Fig. 12, and the result of calculating the wavefront errors as an example is shown in fig. 13.

Wavefront lead and lag, measured in micrometers, is color-coded.

The coding scale is shown next to the error map. The map shows that the lenticonus occupies the central part of the lens with a wavefront lag of up to 7 μm, that is, of the order of ten periods at a wavelength of 700 nm.

The optical transfer function or other statistical estimates of the spatial spectrum can be used to assess the quality of the lens. In the simplest version, it is possible to estimate the spatial spectrum of the distribution of gradients along, for example, one of the axes. The choice of lens quality assessment method is beyond the scope of this invention.

The given example of a device using the proposed method, as well as data processing algorithms are not unique to this device. The proposed method can be implemented in other devices as well.

Claims (7)

FORMULA OF THE INVENTION Koo) The method of synchronous ray-tracing measurement of refractive errors of the eye and refractive inhomogeneity of its lens, based on probing the eye with a thin laser beam sequentially in time, which is characterized by the fact that each point of the entrance aperture of the eye is probed by several, at least two, beams, one of which is central, and the rest are lateral, 35, and the central beam is oriented parallel to the visual axis or with an inclination that compensates for ametropia of the eye, and the side beams are oriented inclined relative to the central beam at an angle specified for each side beam, the images of the projections of the central and side beams are displayed on the photodetector using an optical system focused on retina, measure the coordinates of these images, transferred to the plane 40 of the retina, by the coordinates of the entry into the eye and by the coordinates of the projection of the central beam, the refractive errors of the optical system of the eye as a whole are calculated, and the pairwise difference of the coordinates of the central and side rays at each probing point is used to calculate the refractive inhomogeneity of the lens. KZ i 1 : DE SHE: KA eh -- і "biv KV ni en She onnyi і nt Y і І І І І І І І І ј і p ІЖ Ж ше і r : N : Ge Me ddlezhyuetskefeetesekajjukkoeyukk m g І these sh ІZ ila хх іх 1 and she and She ME child Sh ; and and Ts. m Ya Ki A sh a 143. i bom de yi vi | I rock fo annual hi ko he Be EE Fig. 1 zhozh lk ih shchi ih - - Kuk, for, pr OY I I Ж, Greyu I sleep VYA sha kuvh se Jony yo . Taxes 2 ЭХ dosgntyi fzhyutts pyaniknnnnnn AHMOI 2-2 4 KOS V zaava zvovo oyu so» in nn s nin ne NANNV M WINA da Z Other o she W B VO spzheszhetetinyay se ghy shi Mye full PILU Zhe ek Mi 5 ZI E en va THEY have tnyh ich zok i yn something in Yes es Fig. 2 p. VV Bonn I Dn JI OK Why not! Ka i ami vyka them Shok I drink yutiyu ti Ky m u i y write ch o from B them x Kiintvkyk Fig. He ate with du de J. shetsttk, in their em d ke Um dnenia, nn NIC THEY I e - - ibyakev | je pr i Zh st ptn i i - pam v no neon pane st i pn ni nn i A nyn E MK tt KK UA zar»en mi en zo NYA Bonn x; kh m nn u well 4 Krymta Fig 4 b He tr nn » And what, d sol and be y ukoli, DK s smov KV M . Шими У бук Я на AN Z SVO ож вени я ve a TI PE fer ee KI Я K тоже, зд х Мик кох КА ХО M ва шЧХХУ кати, ! sefku shcha ZA ve V MY DN y, Ku I ikh ikh: t. s, ij zh X tku ; ох и х ох ET, « 215 "dreaming KE r. zi and lens EN gi GY: 6 Her ki FP l zh ok i KO NIE NN: : ! і shi roko 2. dcheeeittotn already Ve nny pisk What X Yeodrnnyunnnnnnnnvnnnn MANTY in the song I And Oi writes d ZHK: and she pk yah 12 - pln U Zh - dv 1 bOVk B: B ; te V le ladan s K 11; - with ON dk do not JUDGE I their BAZ dan and where! mu ii fetdatector Fig. 5 сх и и EI и има: Ka Bk или шен пн они M Я И и Е и 1 4 и Е ИЯ И М В Е И р шх. I BU and M: dX V TEH ICH 3 N KYAZH i V: IZ ih i Koh i cha: EV i scheE N ShKO; what 3 sk! her and Ka! These E that k ZK is and M EK NU and B GE 1 NE 5 a her food her I JE TE: JE: xx them EK KU 5 3 Z xx SKU 5 x them: KK EH her Ek xx xx Z her ZE EUSHN them xx GU EK and EE I SHE I mh Z ; Коши ши Ше: He g NE Ш Ш Ш Ш Ш Ш Ш Ш Ш Ш Ш Ш Ш Ш Ш Ш Ш Ш Ш Ш Ш Ш Ш Ш Ш Ш Ш Ш ЕШ Ш Ш Ш Ш Ш Ш Ш Ш Ш Ш Ш Ш Ш Ш Ш Ш Ш Ш Ш Ш ЗНК УМ Ш Ш Ш Ш Ш Ш Ш Ш Ш Ш Ш Ш Ш Ш Ш Ш Ш Ш Ш Ш Ш Ш Ш Ш Ш ЕШ Ш Ш Ш Ш Ш Ш Ш Ш Ш Ш Ш Щ Ш хх х х У 5 5 х З Z хз ХЕ х Moh GU Ha y х OZ y sen dkno ih pon km, щ Kn es IZ Ko yo Z yiv sya a ; j I and 5 Her i xx This is en x dim in Yashih a U. NON-EFFECTIVE MEANING Fig. 6 Fa y o nih 1 AND MORE WITH ba y sh this ShK, her! gu E: i | 3 I have increased my knowledge from food and from dreams Fig. 7 With i i i I o. EH POM KE OO ZU ! - On DC o DC(( P D D D OYUO yirig. 8 zhu dec KU; / sho A oon a I o E; in : rennya --e Fig. Z ti BE rya a Kon still Ko; their me som y Щche yi Eh I Ya Ku a 7 IN I. Chig. 10 Kk ke r rt ! H 1 ! y i ro Z B Z ze, N i N » N i N i ; A; H with 4 and Z and Me and i i | dssnnny 4 and Shchi Shan: E and ; : i sh : ' V fosnya di zn nn hek ns kn zn ih i E i y : N : te : N E " : ! i sok, 4 N S v Y i oi Her s N i y Z : A Her - N with the 4th; Fig. 1 Fig. 1 Zh. M Nu s Zh ; in KZ B. F in I in F I in KZ shk g what ; х глы и s ши: сеня ДЯ ди я I am: у i ж ж З: ж Ж в у Se kn ny m Ш Ш п b zno Ш Э х no B shik в в вх Ш s - d uznnnkkh ion zn "nene nn V nen dur nnnianyanyaklllyadfiyu SU -i i in in B in PPE 5 in a vv iii iii 5 shi nya Her ;; y Shchy I 5 her I and I y - Kk s 7. ЧУ py NE NN НИ : : , V rya o V Vo ozh ; I am F; In: I; oh K i Z o k i ! g. "be Z - che E inn piy ! dpaertura oka p y tu Fig. 12 ke me | . mio and 5 Fig. 13