WO2011133626A1

WO2011133626A1 - Device and method for calibrating retinoscopes

Info

Publication number: WO2011133626A1
Application number: PCT/US2011/033177
Authority: WO
Inventors: Clinton N. Sims
Original assignee: Sims Clinton N
Priority date: 2010-04-21
Filing date: 2011-04-20
Publication date: 2011-10-27
Also published as: US8272740B2; CA2794611A1; CA2794611C; US20110261319A1

Abstract

A device for calibrating retinoscopes for diverging and /or converging streak and spot retinoscopy and a method for calibrating retinoscopes to produce a given convergence or divergence of light emitted from the retinoscope from a fixed retinoscopic working distance to produce a predetermined pupillary reflex endpoint at neutralization of a refractive error, thereby resulting in a more accurate corrective eye prescriptions and evaluation of the visual system.

Description

DEVICE AND METHOD FOR CALIBRATING RETINOSCOPES

BACKGROUND OF THE INVENTION

This invention relates to devices and methods for measuring and determining the refractive error in eyes and more particularly, a device for calibrating retinoscopes for diverging and/or converging retinoscopy and a method for calibrating retinoscopes using the device.

Retinoscopy is a technique used by practitioners, such as optometrists and ophthalmologists, to obtain an objective measurement of the refractive error of a patient's eyes in order to determine the patient's prescription for spectacles and/or contacts lenses. Varying retinoscopic measurements are frequently obtained with the current retinoscopes. These retinoscopic errors are due the distance between the condensing lens within the retinoscope and filament of the bulb not being standardized and the inability of the examiner to adjust the divergence of the emitted retinoscopy light to their retinoscopic working distance. The divergence of the light rays emitted from all retinoscopes presently on the market is determined by each manufacturer. Subjective refractions using trial frames and phoropters are used as a more accurate alternative for measuring the refractive error. Phoropters are large and expensive pieces of equipment, which means that many practitioners do not have access to them especially in third world countries. Subjective refractions require a feedback from the patient as to whether one lens is clearer than another lens in order to obtain an accurate measurement of the refractive error. Since subjective refractions cannot be used on patients, such as infants, small children, foreign speaking patients and deaf and/mute patients, an objective measurement using retinoscopy is required. Auto-refractors are used frequently in industrialized countries to replace retinoscopy; however the results are inaccurate in many cases, especially in older patients. As a result, many of these patients are dispensed incorrect lenses.

Jack Copeland was the originator of streak retinoscopy as practiced and taught today and designed the Copeland Optec 360 Streak Retinoscope. The technique of streak retinoscopy is illustrated in Videotape No. 5063 for the American Academy of Ophthalmology's Continuing Ophthalmic Video Education series, entitled "Retinoscopy; Plus Cylinder Technique." U. S. Pat. No. 3,597,051 of Copeland illustrates his streak retinoscope assembly which has a thumb-slide adapted to move the power capsule housing the bulb and battery up and down relative to the shaft of the retinoscope. The ridges on the knurl on the power capsule allow one to rotate the power capsule housing the bulb 360°. Advancing the thumb-slide to its upper position causes light rays emanating from the retinoscope to diverge. By contrast convergence of the light rays occurs when thumb-slide is moved to it lower position. The Copeland Optec 360 Streak Retinoscope contains a +20.00D condensing lens and a bi-pin lamp. When the thumb-slide is in its upper position, the filament of the lamp is less than five centimeters from the condensing lens and the rays emanating from the filament and passing through the condensing lens are diverging. Moving the slide to a lower position causes the light rays to converge. The filaments of the light bulbs for the Copeland Optec 360 Streak vary in height which results in differences of the divergence power of the emitted retinoscopic light ranging from 0.00D to 1.00D. Many retinoscopes on the market work in the opposite manner as the Copeland Optec 360 in that converging rays are produced when the knurl is in the up position and diverging rays when the knurl is in the down position.

In retinoscopy , the examiner uses a retinoscope to shine light into the patient' s eye and observes the retinal reflection which is referred to as a pupillary reflex. While moving the streak of light across the pupil the examiner observes the relative movement of the pupillary reflex as they use a phoropter or manually placed lenses over the eye to "neutralize" the pupillary reflex. Streak retinoscopy uses three images to measure the refractive state of the eye. The first image, Image I_x is the luminous streak of the retinoscopic bulb. The second image, Image I₂, is the focus or non- focus of image I_x onto the reflecting membrane of the retina. The reflection of the Image L, produces a third image, Image I₃, the pupillary reflex. The non-focus light of Image 1_{ on the iris is the intercept. The examiner can only see the intercept and the Image I₃. The examiner draws all signals from the intercept and third image, Image I₃, as when to rotate the pupillary reflex to align the astigmatic axis and to add or subtract lenses (+or-) to neutralize a refractive error. The retinoscopic working distanceis the distance between the luminous filament of the light bulb from the pupillary plane of the eye. Clinically, the retinoscopic working distance in conventional retinoscopy is manually measured with a string from the examiner's nose to the spectacle lens plane in the phoropter or trial frame. The principals of spot retinoscopy are the same as streak retinoscopy; the only difference is the pupillary streak is a spot of light instead of a streak. Streak retinoscopy is popular in the United States, South America and Canada and spot retinoscopy in the European countries.

In retinoscopy, upon neutralization of the refractive error, the diverging retinoscopic light rays used in streak and spot retinoscopy are focused into the eye with a spherical lens placed in front of the eye. This spherical lens is called a retinoscopic spherical lens or fogging lens and its focal length is equal to the examiner's retinoscopic working distance. A neutrality reflex, indicating neutralization of the refractive error, occurs when emitted retinoscopic light exits the retinoscopic spherical lens and enters the pupil as parallel light rays and is focused onto the reflecting membrane of the retina. The reflected light then exits the eye as parallel light rays and is focused by the retinoscopic spherical lens into the hole of a mirror or surface of a semi-reflecting mirror within the retinoscope. This endpoint is called "gross retinoscopy." "Net retinoscopy" occurs on removing the retinoscopic spherical lens, thereby allowing the patient's visual focal point to be extended from the mirror to the end of the refracting lane. If the focal lengths of the retinoscopic working distance, the retinoscopic spherical lens and the emitted diverging retinoscopic light are not equal, the pupillary image will be focused in front or behind the mirror, creating myopic and hyperopic retinoscopic errors respectively. When the pupillary reflex is refocused to the hole in the mirror by the retinoscopist to obtain an infinity pupillary reflex, myopic and hyperopic retinoscopic errors are created.

The variability of conventional retinoscopy is due to several factors, which include the exponentially expanding and moving pupillary reflex which becomes infinite and cannot be seen at neutralization of the patient's refractive error, the low luminosity of the pupillary reflex created by the diverging retinoscopic light which is not calibrated to the examiner's retinoscopic working distance and/or the focal length of the retinoscopic spherical lens. Accommodation and pupillary constriction induced by the retinoscopic light, whetlier on or off-axis, further reduce the illumination of the pupillary reflex. Retinoscopy through dilated pupils induces optical aben-ations and peripheral movements that are different and more myopic than the central pupillary reflex. These factors make it difficult to recognize a definitive endpoint and have contributed to the variability and inaccuracy of conventional retinoscopy.

Retinoscopists use a meridional straddle to confirm the accuracy of the retinoscopic endpoint in conventional retinoscopy. The quote below is from the editorial staff of the American Academy of Pediatrics and Strabismus: "In the 25 years that I taught Retinoscopy and in the 45 years that Copeland taught the subject, calibration of the Scope was to be avoided. Why? Because the endpoint did not depend on calibration of the instrument but rather meridional comparison and ability to utilize all of the various steps together to get to the working distance endpoint. " The reason that an accurate meridional straddle with conventional retinoscopy is important is due to the fact that the endpoint image signifying neutralization of the refractive error cannot be seen when focused into the hole in the mirror or mirror. A meridional balance is when the myopic pupillary reflex is under corrected 0.50D to create a hyperopic pupillary reflex, which is easily seen and then overcorrected 0.50D to create a myopic reflex. This process is repeated several times during a retinoscopic examination. Most retinoscopists use the hyperopic reflex as their endpoint which under-corrects the retinoscopic endpoint. As previously described myopic and hyperopic retinoscopic errors occur when the divergence power of the emitted retinoscopic light is not neutralized by the power of the retinoscopic spherical lens and the retinoscopic working distance not being equal to the focal length of the retinoscopic spherical lens. If these three variables are not equal, the retinoscopic endpoint is focused in front of the mirror or beyond the mirror in which case the meridional balance only confirms the accuracy or inaccuracy of the retinoscopic endpoint. The accuracy of the spherical retinoscopic measurement is dependent on the three variables being equal. Statistically, the inaccuracy of the spherical retinoscopic measurement as compared to the measurements of the cylinder and axis supports this theory.

To improve the endpoints of conventional retinoscopy and eliminate other optical problems of conventional retinoscopy Boeder and Kolder developed a retinoscopic technique using parallel light rays emanating from the retinoscope and claimed this produced "neutralization at infinity" or the ability of the patient to read the Snellen chart during retinoscopy. In their formula describing neutralization at infinity, emmetropia or RSR= 1 was achieved when the relative speed of movement of the intercept and pupillary reflex were equal and the pupillary reflex was no less than 2.0mm. This is expressed in the following formula:

RSR = [l- t/I₁]/[l+t/I₃] - 1

RSR= relative speed of pupillary reflex

Ij = focal length of Image I^

I₃ = focal length of Image I₃

t = retinoscopic distance (cm)

Image I = luminous filament of the bulb

Image I3 = pupillary reflex is the reflection of the retinoscopic light Unfortunately, their technique required the retinoscopist to recognize the width of a 2.5mm with-motion pupillary streak as the endpoint, or one no less than 2mm, an unfamiliar unit of measurement to retinoscopists and many of their claims are invalid:

1. The premise that their infinity retinoscopic technique placed the endpoint of neutralization at infinity instead of the aperture of the retinoscope.

2. The intercept and pupillary reflex will move at different speeds if infinity neutralization is not achieved. That is, if I3 is on the myopic side of neutralization, the with-motion pupillary reflex I₃ moves slightly ahead of the intercept and slower if I3 is on the hyperopic side of neutralization. 3. At infinity neutralization, the power of Image I₃ is independent of the retinoscopic working distance.

4. The pupillary reflex is characterized by "well defined borders" and "evenly distributed brightness" only at neutralization.

5. The endpoint of infinity retinoscopy or emmetropia occurs only when Ij = I₃ is incorrect since in converging infinity retinoscopy, Ij can be greater or less or equal to I₃ when emmetropia is obtained.

6. Naming the article "Neutralization at Infinity in Streak Retinoscopy" since neutralization occurs at the examiner's retinoscopic working distance, not infinity.

7. In the derivation of the infinity formula, Image I_j and 1 ₃ are located at the position where the retinoscope is located, not beyond the retinoscope and this makes RSR = ∞, , not 1, when parallel light rays are emitted from the retinoscope.

8. The formula RSR = [1- t/I^]/[ l+t/13] = 1 does not apply to parallel light emitted from the retinoscope, since the formula is derived on the assumption that the focal lengths 1_{ and 1 ₃ will be greater than t, the retinoscopic working distance. In contrast, with parallel light emitted from the retinoscope, RSR is equal to 1 and t is equal to the focal length of I , and 1 ₃ .

On an inter-national scale, the average optical remake of spectacle lenses is 6-10%. These lenses are remade at no cost to the patient. This extrapolates to a financial and efficiency loss to the physician and optical shop as well as a reduction of the patient's opinion of the professional skills obtained in that office. The optical remakes and complaints have not been reduced by the auto-refractors or the present day refraction and/or retinoscopic techniques. Therefore, a need exists for a device and method that eliminates many of the factors responsible for the variability and retinoscopic errors of conventional retinoscopy. More specifically, a need exists for a calibration technique calibrating a retinoscope to the examiner's retinoscopic working distance using either converging or diverging light emanating from the retinoscope.

The relevant prior art includes the following references (U. S. unless stated otherwise):

Patent No. Inventor Issue/Publication Date

5,650,839 Sims 07-22-1997

5,500,698 Sims 03-19-1996

5,430,508 Sims 07-04-1995 ,597,051 Copeland 08-03-1971

SUMMARY OF THE INVENTION The primary objective of the present invention is to improve the accuracy of streak and spot retinoscopy using diverging retinoscopic light rays and converging infinity retinoscopy using converging rays. Infinity retinoscopy is equivalent to "net retinoscopy".

Another objective of the present invention is to provide standardization for retinoscopic endpoints using either converging or diverging light emanating from the retinoscope.

Another objective of the present invention is to improve the accuracy and repeatability of measurements using retinoscopy.

An even further objective of the present invention is to provide more accurate endpoints for retinoscopes which use converging and diverging light rays.

Another objective of the present invention is to decrease the need to dilate patient's pupils for retinoscopy.

Another objective of the present invention is to eliminate the potential errors prevalent in conventional retinoscopy as practiced today.

Another objective of the present invention is to provide a brighter and more defined endpoint through the use of converging and diverging retinoscopic light rays.

Another objective of the present invention is to eliminate the need of a retinoscopic fogging or spherical lens.

An even further objective of the present invention is to eliminate the need to perform a meridional straddle. An even further objective of the present invention is to improve the accuracy of the meridional straddle if performed.

An even further objective of the present invention is to allow a practitioner to obtain more accurate retinoscopic measurements from patients who cannot communicate with the practitioner.

An even further objective of the present invention is to reduce the amount of follow- up appointments for spectacle re-checks due to inaccurate measurements.

An even further objective of the present invention is to provide a quick accuracy check of a patient's glasses.

Another objective of the present invention is to provide a method that is easy to teach to technicians and easy to learn.

The present invention fulfills the above and other objectives by providing an infinity retinoscopic technique using converging rays emitted from the retinoscope and improving the accuracy of retinoscopy which uses diverging rays emitted from the retinoscope by calibrating a manual retinoscope to produce a given convergence or divergence of light ("Image V) emitted from the retinoscope from a fixed retinoscopic working distance (" t ") to produce a predetermined pupillary reflex endpoint ("Image 1 ₃") at neutralization of the refractive error.

Improvement in the accuracy of conventional retinoscopy using diverging light rays can be accomplished by adjusting the divergence of the emitted retinoscopic light to neutralize the power of the retinoscopic fogging lens and using a lens whose focal length is equal to the examiner's retinoscopic working distance. From the following formula, the required divergence of the emitted retinoscopic light can be determined to produce an infinity endpoint pupillary reflex or a +0.50D with-motion endpoint pupillary reflex for one's retinoscopic working distance.

2 L + Image I_x + Image I₃ = t

Image I_j = vergence power of light rays emitted from retinoscope Image I₃ = power of pupillary reflex t = retinoscopic working distance expressed in diopters L = retinosocpic fogging lens

The steps for calibrating a retinoscope for diverging retinoscopy are as follows.

1. First, a circumferential line is made in the knurl area of the power capsule.

2. Next, the examiner's working distance is optically measured by focusing a retinoscope into an emmetropic eye from their retinoscopic working distance by moving the thumb-slide on the retinoscope until a neutrality reflex occurs, holding the thumb-slide in place, focusing the retinoscopic streak onto a wall and measuring the distance between the retinoscope and the wall.

3. With the aid of the calibration chart, the examiner's retinoscopic working distance is matched to the required calibration spherical lens to be placed in front of the retinoscope for calibrating the divergence of the emitted retinoscopic 33177

13

light rays to the examiner's retinoscopic working distance for an infinity or a +0.50D retinoscopic endpoint.

4. The retinoscope is then held from a wall a distance equal to the examiner's retinoscopic working distance and the calibration sphere held in front of the retinoscope. .

5. The thumb-slide is held in its maximal upward position and the diverging light directed or shined through the calibration sphere onto the wall. The light rays are made less diverging by moving the thumb-slide downward until the retinoscopic streak is focused on the wall.

6. When the retinoscopic streak or spot is focused, the thumb slide is held in this position and the infinity or +0.50D calibration plate adjusted on the body of the retinoscope to align the alignment line on the plate with the calibration line above the knurl and then secured into position. The divergence of the emitted retinoscopic light for an infinity or a +0.50D retinoscopic endpoint is now calibrated to the examiner's retinoscopic working distance.

7. After calibration of the retinoscope, the slide bars can be adjusted to maintain the thumb-slide in a fixed position to maintain the calibration of the retinoscope for future retinoscopies.

If the light rays need to be made more diverging to focus the retinoscopic streak onto the wall, the light bulb within the retinoscope is advanced towards the condensing lens to increase the divergence of the emitted retinoscopic light and the above procedures repeated.

Converging infinity retinoscopy eliminates many of the factors responsible for the retinoscopic errors made using conventional retinoscopy. For converging infinity retinoscopy, the required convergence of the emitted retinoscope light to produce a given endpoint pupillary reflex measured in diopters is detenriined from the following formula: Image I, + Image I₃ = t

Image I_j = vergence power of light rays emitted from retinoscope Image I₃ = power of pupillary reflex t = retinoscopic working distance in diopters The steps for calibrating a retinoscope for converging retinoscopy are:

1. A circumferential calibration line in the knurl area of the power capsule which is moved up and down by the thumb-slide.

2. Next, the examiner 's retinoscopic working distance is optically measured by focusing a retinoscope into an emmetropic eye from one's retinoscopic working distance by moving the thumb-slide on the retinoscope until a neutrality reflex occurs and then holding the thumb-slide in place. The retinoscopic light is then focused onto a wall and the distance between the retinoscope and the wall measured.

3. With the calibration chart, the examiner's retinoscopic working distance is matched to the required focal length of the retinoscopic light for performing +0.50 D or +0.75D converging infinity retinoscopy.

4. Next, the retinoscope is placed at the required distance from a wall as specified by the calibration chart, the retinoscopic light rays focused onto the wall and the thumb-slide secured in place.

5. A calibration plate is attached to the side of the retinoscope, aligning the +0.50D or +0.75D alignment line with the circumferential calibration line above the knurl to mark the position of the power capsule housing the bulb for future converging infinity retinoscopies. 6. After calibration of the retinoscope, the slide bar can be adjusted to maintain the thumb-slide in a fixed position to maintain the calibration of the retinoscope for future retinoscopies.

The above and other objects, features and advantages of the present invention should become even more readily apparent to those skilled in the art of retinoscopy upon reading the following detailed description in conjunction with the drawings wherein shown and the described illustrative embodiments of the invention.

BRIEF DESCRIPTION OF THE DRAWINGS

FIG. 1 is a side partial cutaway view of a condensing lens, a mirror, a lam , a power capsule with a knurl for rotating the power capsule and a thumb-slide which moves the power capsule housing the lamp;

FIG. 2 is a schematic of the knurl area on the power capsule with a circumferential line;

FIG. 3 is a schematic view of light rays emanating from a retinoscope in a diverging pattern;

FIG.4 is a schematic view of light rays emanating from a retinoscope in a converging pattern;

FIG. 5 is a flow chart for optically measuring one's retinoscopic working distance;. FIG. 6 is a chart for calibrating the retinoscope using diverging rays for an infinity retinoscopic and +0.50D endpoints and for calibrating a retinoscope using converging rays for +0.50D and +0.75D retinoscopic endpoints;

FIG.7-A is an attachable plate for retrofitting a retinoscope for a +0.50D retinoscopic endpoint using converging rays calibrated to the examiner's retinoscopic working distance;

FIG. 7-B is an attachable plate for retrofitting a retinoscope for a +0.75D retinoscopic endpoint using converging rays calibrated to the examiner's retinoscopic working distance;

FIG. 7-C is an attachable plate for retrofitting a retinoscope for an infinity retinoscopic endpoint using diverging rays calibrated to the examiner's retinoscopic working distance;

FIG.7-D is an attachable plate for retrofitting a retinoscope for a +0.50D retinoscopic endpoint using diverging rays calibrated to the examiner's retinoscopic working distance;

FIG. 8 is a flow chart showing the steps for calibrating a retinoscope for a +0.50D retinoscopic endpoint using converging retinoscopic light rays calibrated to the examiner's retinoscopic working distance;

FIG. 8- A is a retinoscope showing proper attachment of the +0.50D converging plate after calibration of retinoscope light rays to the examiner's retinoscopic working distance;

FIG. 9 is a flow chart showing the steps for calibrating a retinoscope for a +0.75D pupillary reflex endpoint using converging retinoscopic light rays;

FIG. 9-A is a retinoscope showing proper attachment of the +0.75D converging plate after calibration of retinoscopic light rays to the examiner's retinoscopic working distance;

FIG. 10 is a flow chart showing the steps for calibrating a retinoscope for an infinity retinoscopic endpoint using diverging retinoscopic light rays calibrated to the examiner's retinoscopic working distance;

FIG. 10- A is a retinoscope showing proper attachment of the infinity diverging plate after calibration of the retinoscopic light rays to the examiner's retinoscopic working distance;

FIG. 11 is a flow chart showing the steps for calibrating a retinoscope for a +0. 0D retinoscopic endpoint using diverging retinoscopic light rays calibrated to the examiner's retinoscopic working distance;

FIG. 11-A is a retinoscope showing the proper attachment of the +0.50D diverging plate after calibration of retinoscopic light rays to the examiner's retinoscopic working distance; FIG. 12 is a flow chart showing the steps for performing a calibration check of a retinoscope emanating converging rays calibrated to the examiner's retinoscopic working distance;

FIG. 13 is a rear view of a retinoscope showing a slide bar which can be adjusted to maintain the thumb-slide in a fixed position to maintain the calibration of the retinoscope for future retinoscopies;

FIG. 14 is a side view of a retinoscope showing a slide bar which can be adjusted to maintain the thumb-slide in a fixed position to maintain the calibration of the retinoscope for future retinoscopies; and FIG. 15 is a front perspective view of a bulb extender of the present invention.

DESCRIPTION OF THE PREFERRED EMBODIMENTS

1. retinoscope 31. +0.75D converging plate

2. thumb-slide 32. infinity diverging plate

3. condensing lens 33. +0.50D diverging plate

4. lamp 34. optically measure the

5. filament retinoscopic working distance

6. handle of retinoscope 35. Using the calibration chart, match

7. hole in mirror the distance the retinoscope must

8. mirror be held from wall to the

9. knurl on power capsule retinoscopic working distance

10. power capsule 36. place retinoscope at required

11. calibration line on power capsule distance from a wall

12. retinoscopic light rays 37. focus retinoscope and hold thumb-

13. diverging pattern slide in place

14. converging pattern 38. align the alignment on plate with

15. optical measurement of the calibration line

retinoscopic working 39. secure +0.50D converging plate to distance: retinoscope

16. hold thumb-slide in place 40. secure +0.75D converging plate

and focus retinoscope to retinoscope

onto wall. 41. using calibration chart, match

17. measure distance between retinoscopic working distance to

retinoscope and wall power of calibration lens required

18. calibration chart 42. place retinoscope a distance from a

19. retinoscopic working wall equal to the retinoscopic

distance (em) working distance

20. calibration sphere required for 43. place calibration sphere in front of

calibrated infinity endpoint retinoscope

using diverging light rays 44. if retinoscopic light fails to focus,

21. calibration sphere required for move bulb towards condensing

calibrated +0.50D endpoint lens and refocus reflex onto wall using diverging light rays 45. align calibration line with

22. required focal length of alignment line on the infinity

retinoscopic diverging plate

light for +0.50D endpoint using 46. secure infinity diverging plate to converging light rays retinoscope

23. required focal length of 47. align calibration line with

retinoscopic alignment line on the +0.50D

light for +0.75D endpoint using diverging plate

converging light rays 48. secure the +0.50D diverging plate

24. plate to retinoscope

25. +0.50D converging plate 49. assume one's routine retinoscopic

26. front surface of calibration plate working distance

27. rear surface of calibration plate 50. check alignment of calibration and

28. alignment line alignment lines

29. attachment means 51. upper slide bar

30. adjustment means 52. bulb extender

53. aperture

54. post

55. locking means

56. lower slide bar

With reference to FIG. 1, a side partial cutaway view of a retinoscope 1 having a thumb-slide 2 and a condensing lens 3 and a lamp 4 is shown. The lamp 4 includes a linear filament 5 designed to create a "streak" image which is reflected from a patient's retina and seen by a practitioner, such as an optometrist or ophthalmologist. The thumb-slide 2 moves the power capsule housing the lamp 4 moves up and down along a handle of the retinoscope

6 so that when the thumb-slide 2 is in a maximal upward position, the filament 5 is less than 5cm from lens 3 which has an approximate power of +20.00D. When the thumb-slide 2 is in a maximal down position, the filament 5 is approximately 6.6cm from the the lamp 4. The practitioner can view the light rays reflected from the patient's retina through a small opening

7 in mirror 8. The examiner can only see the retinoscopic light on the patient's iris and the reflected pupillary reflex. The examiner nevertheless is able to move the pupillary reflex toward neutralization by the movement and orientation of the pupillary reflex. The examiner draws all of the retinoscopic signals from the pupillary reflex, that is, when to change or rotate the retinoscopic streak to achieve neutralization of the spherical and cylindrical error.

With reference to FIG. 2, calibration of the retinoscope requires a calibration line 11 in the knurl area 9 on the power capsule 10 to align the Plates 7 A and 7B for converging infinity retinoscopy and Plates 7C and 7D for diverging retinoscopy after the retinoscope is calibrated to the specifications in the Calibration Chart 18.

With reference to FIG. 3, a schematic view of light rays 12 emanating from a retinoscope 1 in a diverging pattern 13 is shown. In diverging retinoscopy the lamp 4 is within the focal length of lens 3. The proximity of the lamp 4 to the lens 3 causes the light rays 12 emitted from the retinoscope 1 to spread out into a diverging pattern 13.

The retinoscopic technique of identifying and neutralizing a refractive error is the same with calibrated diverging retinoscopy as with conventional retinoscopy. Calibrated diverging retinoscopy differs from conventional retinoscopy in that the divergence of the emitted retinoscopic light rays 12 is calibrated to one's retinoscopic working distance. The endpoint of calibrated diverging retinoscopy can be an infinity retinoscopic endpoint which is identical to the endpoint of conventional retinoscopy or a +0.50D with-motion pupillary reflex.

With reference to FIG. 4, a schematic view of light rays 12 emanating from a retinoscope 1 in a converging pattern 14 is shown. In converging retinoscopy, the lamp 4 is displaced beyond the focal length of lens 3. The increased distance of the lamp 4 from the lens 3 causes the light rays 12 emitted from the retinoscope 1 to focus into a converging pattern 14.

With reference to FIG. 5, a flow chart showing the steps for measuring a retinoscopic working distance for use in calibrating a retinoscope for converging and diverging retinoscopy is shown. The examiner's retinoscopic working distance is optically measured by focusing the retinoscopic light into an emmetropic eye using the thumb slide until a neutrality reflex occurs 15. Then, the retinoscopist holds the thumb-slide on the retinoscope in place and the emitted retinoscopic light is focused onto a wall by moving the retinoscope towards the wall until the streak is in focus 16. Finally, the distance between the wall and retinoscope is measured to obtain the examiner's retinoscopic working distance 17.

With reference to FIG. 6, a calibration chart 18 is shown. The calibration chart 18 lists the retinoscopic working distance in centimeters 19 and the required power of the calibration lens to be held in front of the retinoscope, which is held from a wall a distance equal to the examiner ' s retinoscopic working distance 19 , in order to calibrated the diverging retinoscopic light for an infinity endpoint 20 and a +0.50D endpoint 21. Chart 18 also lists the distance a retinoscope must be held from a wall to calibrated the retinoscope using converging light for a +0.50D endpoint 22 and a +0.75D endpoint 23, when performing retinoscopy from one's retinoscopic working distance.

With reference to FIG. 7-A, an attachable plate 24 for retrofitting a retinoscope 1 when calibrated for a +0.50D with-motion endpoint pupillary reflex using converging rays 14 emitted from the retinoscope 1 is shown. The plate 24 shown here is a +0.50D converging plate 25 and is used when the converging light emanating from the retinoscopies is calibrated for a +0.50D with-motion retinoscopic endpoint, as shown further in FIG. 8. The +0.50D converging plate 25 has a front surface 26, a rear surface 27 and an alignment line 28. The plate 24 is attachable to the retinoscope via an attachment means 29, such as screws nuts, etc. The plate 24 is moveable via an adjustment means 30, such as a slot that moves along a screw, so that a user may adjust the alignment line 28 up or down to be in alignment with the calibration line 11 on the power capsule 10. After the retinoscope is calibrated and plate 24 secured into position, the alignment line 28 on plate 24 allows the retinoscopist to know where to place the calibration line 11 on the power capsule 10 to obtain a +0.50D retinoscopic endpoint using converging light, as shown further in FIG. 8-A.

With reference to FIG. 7-B, an attachable plate 24 for retrofitting a retinoscope 1 when calibrated for a +0.75D with-motion retinoscopic reflex using converging light rays 14 emitted from the retinoscope 1 is shown. The plate 24 shown here is a +0.75D converging plate 31 and is used when the converging light 14 emanating from the retinoscope is calibrated for a +0.75D with-motion retinoscopic endpoint, as shown further in FIG. 9. The +0.75D converging plate 31 has a front surface 26, a rear surface 27 and an alignment line 28. The plate 24 is attachable to the retinoscope via an attachment means 29, such as screws nuts, etc. The plate 24 is moveable via an adjustment means 30, such as a slot that moves along a screw, so that a user may adjust the alignment line 28 up or down to be in level with the calibration line 11 on the power capsule 10. After the retinoscope is calibrated and plate 24 secured into position, the alignment line 28 on plate 31 allows the retinoscopist to know where to place the calibration line 11 on the power capsule 10 to obtain a +0.75D retinoscopic endpoint using converging light, as shown further in FIG. 9-A.

With reference to FIG. 7-C, an attachable plate 24 for retrofitting a retinoscope 1 when calibrated for an infinity endpoint using diverging light rays 13 emitted from the retinoscope 1 is shown. The plate 24 shown here is an infinity endpoint diverging plate 32 and is used when the diverging light 13 emitted from the retinoscope is calibrated for an infinity retinoscopic endpoint, as shown further in FIG. 10. The infinity diverging plate 32 has a front surface 26, a rear surface 27 and an alignment line 28. The plate 24 is attachable to the retinoscope via an attachment means 29 such as screws, adhesive, nuts, etc, The plate 24 is moveable via an adjustment means 30, such as a slot that moves along a screw, so that a user may adjust the alignment line 28 up or down to be level with the calibration line 11 on the power capsule 10 after the retinoscope is calibrated. After the retinoscope is calibrated and plate 32 secured into position, the alignment line 28 on plate 32 allows the retinoscopist to know where to place the calibration line 11 on the power capsule 10 to perform retinoscopy with diverging light rays to obtain an infinity retinoscopic endpoint adjusted to one retinoscopic working distance as shown further in FIG. 10-A.

With reference to FIG. 7-D, an attachable plate 24 for retrofitting a retinoscope 1 when calibrated to a +0.50D with- motion pupillary reflex endpoint using diverging retinoscopic light rays 13 is shown. The plate 24 shown here is a diverging plate 33 and is used when the diverging light emanating from the retinoscope is calibrated for a +0.50D with motion retinoscopic endpoint as shown further in FIG. 11. The +0.50D diverging plate 33 has a front surface 26, a rear surface 27 and an alignment line 28. The plate 24 is attachable to the retinoscope via an attachment means 29, such as screws, adhesive, nuts, etc. The plate 24 is moveable via an adjustment means 30, such as a slot that moves along a screw, so that a user may adjust the alignment line 28 up or down to be in alignment with the calibration line 11 on the power capsule 10 after the retinoscope is calibrated. The alignment line 28 on plate 33 allows the retinoscopist to know where to place the calibration line 11 on the power capsule 10 to perform retinoscopy with diverging light rays to obtain a +0.50D retinoscopic endpoint adjusted to one retinoscopic working distance as shown further in FIG. 11-A. With reference to FIG. 8, a flow chart showing the steps for calibrating a retinoscope for a +0.50D with-motions retinoscopic endpoint using converging retinoscope light rays 14 is show. First, the retinoscopic working distance is optically measured 34 as shown in FIG. 5. Then, the required focal length of the emitted retinoscope light for a +0.50D retinoscopic endpoint is determined 35 using the calibration chart 18 illustrated in FIG. 6. For example, if the retinoscopic working distance is 67cm, the required focal length of the emitted retinoscopic light is 100cm. Next, the retinoscope is placed at the proper focal length from a wall 36 and focused 37. Finally 38, the alignment line 28 on the +0.50D converging plate 25 is aligned with the calibration line 11 on the power capsule 10 as shown further in Fig. 8-A and secured 39.

With reference to FIG. 8-A, a retinoscope 1 having a +0.50D converging plate 25 attached thereto is shown. The retinoscope 1 has been calibrated for a +0.5 ODpupillary reflex endpoint using converging retinoscope light rays 14. The technique for performing retinoscope using a retinoscope calibrated for a +0.50D retinoscopic endpoint is the same as in conventional retinoscopy, except that the calibration line 11 on the power capsule 10 is level with the alignment line 28 on the +050D converging plate 25 and the retinoscopic endpoint is a +0.50D with-motion retinoscopic reflex with the +0.50D pupillary reflex and intercept moving in unison.

With reference to FIG. 9, a flow chart showing the steps for calibrating a retinoscope for a +0.75D with-motions retinoscopic endpoint using converging retinoscope light rays 14 is show. First, the retinoscopic working distance is measured 34 as shown in FIG. 5. Then, the required focal length of the emitted retinoscope light is detemiined 35 using the calibration chart 18 illustrated in FIG. 6. For example, if the retinoscopic working distance is 67cm, the required focal length of the emitted retinoscopic light is 133cm. Next, the retinoscope is placed at the proper focal length from a wall 36 and focused 37 and the thumb- slide held in position. Finally 38, the alignment line 28 on the +0.75D converging plate 31 is aligned with the calibration line 11 on the power capsule 10 of retinoscope 1 as shown further in Fig. 8-A and secured 40.

With reference to FIG. 9-A, a retinoscope 1 having a +0.75D converging plate 31 attached thereto is shown. The retinoscope 1 has been calibrated for a +0.75D endpoint using converging retinoscopic light rays 14. The technique for performing retinoscopy using a retinoscope calibrated for a +0.75D retinoscopic endpoint is the same as in conventional retinoscopy, except the calibration line 11 on power capsule 10 is level with the alignment line 28 on the +075D converging plate 31 and the retinoscopic endpoint is a +0.75D retinoscopic and moves in unison with the intercept.

With reference to FIG.10, a flow chart showing the steps for calibrating a retinoscope 1 for an infinity retinoscopic endpoint using diverging retinoscopic rays 13 is shown. First, the retinoscopic working distance 34 is measured in centimeters, as shown in FIG. 5. Next

41, the retinoscopic working distance in centimeters 19 is matched to the power of the calibration lens required 20 using the calibration chart 18,. For example, if the retinoscopic working distance is 67cm, the power of calibration sphere would be +3.00D. Next, the retinoscope 1 is placed at a distance from the wall equal to the retinoscopic working distance

42. Next, the +3.00D calibration sphere as determined from 41 is placed in front of the retinoscope 43. With the thumb-slide 2 in the maximal upward position and the diverging retinoscopic light shinning through the +3.00D calibration spherical lens, the thumb-slide 2 is lowered until the retinoscopic streak is focused onto the wall 37. If the retinoscopic streak fails to focus onto the wall, the bulb 4 is advanced towards the condensing lens 3 within the retinoscope 1 and the procedure repeated until the retinoscopic streak is focused onto the wall, 44. Next 45, the alignment line 28 on the infinity diverging plate 32 is aligned with the calibration line 11 on the power capsule 10 and secured in position 46 as shown further in FIG.10-A.

With reference to FIG. 10-A, a retinoscope 1 having an∞ diverging plate 32 attached thereto is shown. The retinoscope 1 has been calibrated for an infinity retinoscopic endpoint using diverging retinoscope light rays 13. The technique for performing retinoscopy using an infinity retinoscopic endpoint with the emitted retinoscopic light rays calibrated to the examiner's retinoscopic working distance is the same as in conventional retinoscopy, except that the calibration line 11 on the power capsule 10 is level with the measuring line 28 on the infinity plate 32.

With reference to FIG. 11 , a flow chart showing the steps for calibrating a retinoscope

1 for a +0.50D retinoscopic endpoint using diverging retinoscope light rays 13 is show.

First the working distance is measure centimeters 34, as shown in FIG. 5. Next 41, the retinoscopic working distance in centimeters 19 is matched to the power of the calibration lens required 21 using the calibration chart 18. For example, if the retinoscopic working distance is 67cm the power of the calibration sphere would be +3.50D. Next, the retinoscope 1 is placed at a distance from the wall equal to the retinoscopic working distance 42. Next, the +3. SOD sphere is placed in front of the retinoscope 43. With the thumb-slide

2 in the maximal upward position and the diverging retinoscopic light shinning through the +3.50D calibration lens, the thumb-slide 2 lowered until the retinoscopic streak is focused onto the wall 37. If the retinoscopic streak fails to focus onto the wall, the bulb 4 is displaced toward the +20D condensing lens 3 within the retinoscope and the procedure repeated until the retinoscopic streak is focused onto the wall, 44. Next 47, the alignment line 28 on +0.50D diverging plate 33 is aligned with the calibration line 11 on the power capsule 10 and secured in position 48 as shown further in FIG.ll-A. With reference to FIG.ll-A, a retinoscope 1 having a +0.50D diverging plate 33 attached thereto is shown. The retinoscope 1 has been calibrated for a +0.50D retinoscopic endpoint using diverging light rays 13 exiting the retinoscope. The technique for performing retinoscopy using a retinoscope calibrated to one's retinoscopic working distance for a +0.50D retinoscopic endpoint is the same as conventional retinoscopy except the retinoscopic endpoint is a +0.50D with-motion retinoscopic endpoint and the calibration line 11 is level with the alignment line 28. In contrast to the +0.50D retinoscopic endpoint produced with converging rays emitted from the retinoscope in FIG. 8-A, with diverging rays the +0.50D retinoscopic endpoint moves faster than the intercept.

With reference to FIG.12, a flow chart showing the steps for performing a calibration check on retinoscopes calibrated to emit converging rays 14 as shown in FIGS. 8-A and 9-A is shown. First, the practitioner assumes his or her routine retinoscope distance 49. Then the practitioner lowers the thumb-slide 2 of the retinoscope from its maximal upward position until a neutrality reflex is seen in an emmetropic eye 12 and holds the thumb-slide in this position 15. If the calibration line 11 on the power capsule 10 is level with the alignment line 28 on the converging plates 25 or 31, the retinoscope is calibrated 50. In the Copeland Optec 360 Streak Retinoscope, the thumb-side is kept in the most superior position by a spring.

With reference to FIGS. 13 and 14, a rear view and a side view, respectively, of a retinoscope 1 having an upper slide bar 51 attached to the body of the retinoscope and located superiorly to the thumb-slide 2 thereto and having a lower slide bar 56 attached to the body of the retinoscope and located inferiorly to the thumb-slide 2 is shown. The slide bars 51, 56 are attachable to the retinoscope via an attachment means 29, such as screws, nut, etc. The slide bars 51, 56 are moveable via an adjustment means 30, such as a slot that moves along a post 54. After the retinoscope is calibrated, the slide bars 51, 56 are adjusted to touch the top and bottom, respectively, of the thumb-slide 2 and locked in place via a locking means 55, such as a screw, etc., to prevent the thumb-slide 2 from moving upward or downward.

Although a practitioner may use a +0.50D retinoscopic endpoint or a +0.75D retinoscopic endpoint, the +0.50D retinoscopic endpoint is easier, faster and more convenient to confirm than the +0.75D retinoscopic endpoint, since during retinoscopy, the neutrality reflex is displaced 2 lenses from the +0.50D retinoscopic endpoint and 3 lenses from the +0.75D retinoscopic endpoint.

Finally with reference to FIG. 15, a front perspective view of a bulb extender 52 of the present invention is shown. The bulb extender 52 acts as a spacer to increase the height of a lamp 4 and filament 5 within the retinoscope 1. The bulb extender 52 elevates lamps 4 having shorter filaments 5 towards the lens 3 in order to increase the divergence of emitted retinscopic light. The bulb extender 52 has at least one aperture 53 to allow electronic communication between a power source of the retinoscope land the filment 5.

It is to be understood that while a preferred embodiment of the invention is illustrated, it is not to be limited to the specific form or arrangement of parts herein described and shown. It will be apparent to those skilled in the art that various changes may be made without departing from the scope of the invention and the invention is not to be considered limited to what is shown and described in the specification and drawings.

Claims

Having thus described my invention, I claim:

1. A calibration plate for calibrating a retinoscope having a handle, a lamp housed within a power capsule, a lens located above the lamp, a thumb-slide for sliding the power capsule housing the lamp, said calibration plate comprising: a flat piece of material having a front surface and a rear surface;

at lest one measurement line located on the front surface; and

an attachment means for attaching said plate to the retinoscope.

2. The calibration plate of claim 1 wherein:

said slidable calibration plate is attached to the retinoscope, thereby allowing a user to adjust the placement of the alignment line on the calibration plate and measurement line in relation to the calibration line on the power capsule.

3. The calibration plate of claim 1 wherein:

said measurement line is located at a predetermined position on the calibration plate for calibrating a retinoscope for a +0.50D endpoint using converging retinoscopy.

4. The calibration plate of claim 1 wherein:

said measurement line is located at a predetermined position on the calibration plate for calibrating a retinoscope for +0.75D endpoint using converging retinoscopy.

5. The calibration plate of claim 1 wherein: said measurement line is located at a predetermined position on the calibration plate for calibrating a retinoscope for +0.50D endpoint using diverging retinoscopy.

6. The calibration plate of claim 1 wherein:

said measurement line is located at a predetermined position on the calibration plate for calibrating a retinoscope for an infinity endpoint using diverging retinoscopy.

7. The calibration plate of claim 1 wherein:

the lamp creates a spot image.

8. The calibration plate of claim 1 wherein:

the lamp creates a streak image.

9. The calibration plate of claim 1 further comprising:

an upper slide bar located above the thumb-slide which can be adjusted to maintain the thumb-slide in position to mamtain the calibration of the retinoscope for future retinoscopies; and

a lower slide bar located below the thumb-slide which can be adjusted to maintain the thumb-slide in position to maintain the calibration of the retinoscope for future retinoscopies.

10. A method for calibrating a retinoscope having a handle, a lamp housed within a power capsule, a lens located above the lamp, a thumb-slide for sliding the power capsule housing the lamp up or down using a calibration plate having a flat piece of material having a front surface and a rear surface with at least one measurement line located on the front surface; said method comprising the following steps:

a. measuring one's retinoscopic working distance using the retinoscope; b. from calibration chart determining required focal length with said retinoscopic working distance;

c. placing the retinoscope at a distance from a wall that's equal to the focal length; and

d. focusing the retinoscope onto the wall;

e. placing a calibration line on the power capsule of the retinoscope so the alignment line on calibration plate is even with the calibration line on power capsule housing the lamp.

11. The method of claim 10 wherein step a comprises the following steps: a. focusing the retinoscope into an emmetropic eye;

b. focusing a focal length of a retinoscope streak emanating from the retinoscope onto a wall; and

c. measuring the distance between the retinoscope and the wall.

12. The method of claim 10 wherein step e further comprises the following step:

adjusting the placement of the calibration plate on the retinoscope so that the alignment line is even with the calibration line onto the power capsule housing the lamp.

13. The method of claim 10 further comprising the following steps after d a. assuming a routine retinoscopic working distance;

b. adjusting the thumb-slide until a neutrality reflex is seen in the patient; and

c. checking that the alignment line is even with the calibration line.

14. The method of claim 10 wherein:

If the working distance equals 50cm then the required focal length of the retinoscopic light will equal 67cm for calibrating the retinoscope to perfonn +0.50D converging retinoscopy.

15. The method of claim 10 wherein:

If the working distance equals 54cm then the required focal length of the retinoscopic light will equal 73cm for calibrating the retinoscope to perform +0.50D converging retinoscopy.

16. The method of claim 10 wherein:

If the working distance equals 57cm then the required focal length of the retinoscopic light will equal 80cm for calibrating the retinoscope to perform +0.50D converging retinoscopy.

17. The method of claim 10 wherein: If the working distance equals 62cm then the required focal length of the retinoscopic light will equal 89cm for calibrating the retinoscope to perform +0.50D converging retinoscopy.

18. The method of claim 10 wherein:

If the working distance equals 67cm then the required focal length of the retinoscopic light will equal 100cm for calibrating the retinoscope to perform +0.50D converging retinoscopy.

19. The method of claim 10 wherein:

If the working distance equals 73 cm then the required focal length of the retinoscopic light will equal 1 15cm for calibrating the retinoscope to perform +0.50D converging retinoscopy.

20. The method of claim 10 wherein:

If the working distance equals 80cm then the required focal length of the retinoscopic light will equal 133cm for calibrating the retinoscope to perfonn +0.50D converging retinoscopy.

21. The method of claim 10 wherein:

If the working distance equals 50cm then the required focal length of the retinoscopic light will equal 80cm for calibrating the retinoscope to perfonn +0.75D converging retinoscopy.

The method of claim 10 wherein: If the working distance equals 54cm then the required focal length of the retinoscopic light will equal 89cm for calibrating the retinoscope to perform +0.75D converging retinoscopy.

23. The method of claim 10 wherein:

If the working distance equals 57cm then the required focal length of the retinoscopic light will equal 100cm for calibrating the retinoscope to perform +0.75D converging retinoscopy.

24. The method of claim 10 wherein:

If the working distance equals 62cm then the required focal length of the retinoscopic light will equal 1 15cm for calibrating the retinoscope to perform +0.75D converging retinoscopy.

25. The method of claim 10 wherein:

If the working distance equals 67cm then the required focal length of the retinoscopic light will equal 133cm for calibrating the retinoscope to perform +0.75D converging retinoscopy.

26. The method of claim 10 wherein:

If the working distance equal 73cm then the required focal length of the retinoscopic light will equal 161 cm for calibrating the retinoscope to perform +0.75D converging retinoscopy.

The method of claim 10 wherein: If the working distance equals 80cm then the required focal length of the retinoscopic light will equal 200cm for calibrating the retinoscope to perform +0.75D converging retinoscopy.

28. The method of claim 10 wherein:

the lamp creates a spot image.

29. The method of claim 10 wherein:

the lamp creates a streak image.

30. The method of claim 10 further comprising the following steps after d of:

locking the thumb-slide in position to maintain the calibration of the retinoscope for future retinoscopies.

31. The method of claim 10 further comprising the step of:

placing a bulb extender under the lamp in order to elevate the lamp towards the lens and increase divergence of emitted retinscopic light.

32. A method for calibrating a retinoscope having a handle, a lamp housed within a power capsule, a lens located above the lamp, a thumb-slide for sliding the power capsule housing the lamp up or down using a calibration plate having a flat piece of material having a front surface and a rear surface with at least one measurement line located on the front surface; said method comprising the following steps: measuring one's retinoscopic working distance using the retinoscope; determining an equivalent sphere with same focal length equal to retinoscopic working distance;

placing the retinoscope at a distance from a wall equal to the focal length;

placing a sphere with twice the power determined in step b in front of the retinoscope;

focusing the retinoscope; and

placing the alignment line on the calibration plate even with the marker line on power capsule housing the lamp.

33. The method of claim 32 wherein step a comprises the following steps: a. focusing the retinoscope into an emmetropic eye;

c. measuring the distance between the retinoscope and the wall.

34. The method of claim 32 wherein step f further comprises the following step:

adjusting the placement of the calibration plate on the retinoscope so that the alignment line is even with the calibration line on the power capsule housing the lamp.

35. The method of claim 32 wherein:

If the working distance equals 50cm, then the sphere power will equal +4.00D for calibrating the retinoscope to perform diverging retinoscopy with an infinity endpoint.

36. The method of claim 32 wherein:

If the working distance equals 54cm, then the sphere power will equal +3.75D for calibrating the retinoscope to perform diverging retinoscopy with an infinity endpoint.

37. The method of claim 32 wherein:

If the working distance equals 57cm, then the sphere power will equal +3.50D for calibrating the retinoscope to perform diverging retinoscopy with an infinity endpoint.

38. The method of claim 32 wherein:

If the working distance equals 62cm, then the sphere power will equal +3.25D for calibrating the retinoscope to perform diverging retinoscopy with an infinity endpoint.

39. The method of claim 32 wherein:

If the working distance equals 67cm, then the sphere power will equal +3.00D for calibrating the retinoscope to perform diverging retinoscopy with an infinity endpoint.

40. The method of claim 32 wherein:

If the working distance equals 73cm, then the sphere power will equal +2.75D for calibrating the retinoscope to perform diverging retinoscopy with an infinity endpoint.

41. The method of claim 31 wherein:

If the working distance equals 80cm, then the sphere power will equal +2.50D for calibrating the retinoscope to perform diverging retinoscopy with an infinity endpoint.

42. The method of claim 32 further comprising the following steps after f of: a. assuming a routine retinoscopic working distance;

b. placing a sphere with a focal length equal to the retinoscopic working distance in front of an emmetropic eye;

c. adjusting the thumb-slide until a neutrality reflex is seen in the patient; and

d. checking that the alignment line on the calibration plate is level with the calibration line on the power capsule.

43. The method of claim 32 wherein:

If the working distance equals 50cm, then the sphere power will equal +4.50D for calibrating the retinoscope to perform diverging retinoscopy with a +0.50D endpoint.

44. The method of claim 32 wherein:

If the working distance equals 54cm, then the sphere power will equal +4.25D for calibrating the retinoscope to perform diverging retinoscopy with a +0.50D endpoint.

45. The method of claim 32 wherein:

If the working distance equals 57cm, then the sphere power will equal +4.00D for calibrating the retinoscope to perform diverging retinoscopy with a +0.50D endpoint.

46. The method of claim 32 wherein:

If the working distance equals 62cm, then the sphere power will equal +3.75D for calibrating the retinoscope to perform diverging retinoscopy with a +0.50D endpoint.

47. The method of claim 32 wherein:

48. The method of claim 32 wherein:

If the working distance equals 73cm, then the sphere power will equal +3.25D for calibrating the retinoscope to perform diverging retinoscopy with a +0.50D endpoint.

49. The method of claim 32 wherein:

If the working distance equals 80cm, then the sphere power will equal +3.00D for calibrating the retinoscope to perform diverging retinoscopy with a +0.50D endpoint.

50. The method of claim 32 further comprising the step of:

adjusting the placement of the calibration plate on the retinoscope so that the measurement line is even with the calibration line on the power capsule housing the lamp.

51. The method of claim 32 wherein:

the lamp creates a spot image.

52. The method of claim 32 wherein:

the lamp creates a streak image.

53. The method of claim 32 further comprising the following steps after d of:

54. The method of claim 32 further comprising the step of: