METHOD AND APPARATUS FOR EVALUATING THE PERFORMANCE CHARACTERISTICS OF ENDOSCOPES

Abstract: In a method and apparatus for evaluating the performance characteristics of fiber-optic endoscopes, a beam of light defining a predetermined intensity pattern is transmitted through the endoscope from a tip end through an eyepiece end of the endoscope. The intensity pattern of the beam defines either a uniform intensity, or an intensity which varies sinusoidally in a predetermined direction across the beam. The following tests are performed in order to evaluate both the optical fibers and the lens system of the endoscope, and the intensity pattern is selected in accordance with the requirements of the respective test: (i) a light loss test, (ii) a reflective symmetry test, (iii) a lighted fibers test, (iv) a geometric distortion test, and (v) a MTF test. A video system (22) generates signals indicative of the optical intensity of the beam after transmission through the endoscope at each of the plurality of predetermined locations within the beam. The video signals are in turn evaluated in accordance with the selected tests in order to provide graphical and numerical indicia of the optical performance characteristics of the endoscope.

Description: METHOD AND APPARATUS FOR EVALUATING THE PERFORMANCE CHARACTERISTICS OF ENDOSCOPES Field Of The Invention The present invention relates to systems for testing endoscopes, and more specifically to systems for evaluating the optical performance characteristics of fiber optic endoscopes . Cross Reference To Related Applications Some of the matter contained herein is disclosed in U.S. Patent Application Serial No. 08/822,330, entitled "METHOD AND APPARATUS FOR PERFORMING MODULATION TRANSFER FUNCTION TESTS ON ENDOSCOPES" (Attorney Docket No. 5509-02); U.S. Patent Application Serial No. 08/821,601, entitled "APPARATUS FOR EVALUATING THE PERFORMANCE CHARACTERISTICS OF ENDOSCOPES" (Attorney Docket No. 5509-03); and U.S. Patent Application Serial No. 08/822,283, entitled "AUTOMATED METHOD AND APPARATUS FOR EVALUATING THE PERFORMANCE CHARACTERISTICS OF ENDOSCOPES" (Attorney Docket No. 5509- 04), each of which was filed in the U.S. Patent & Trademark Office on March 20, 1997, is assigned to the Assignee of the present invention, and is hereby expressly incorporated by reference as part of the present disclosure. Background Of The Invention A typical endoscope comprises a cylindrical stainless steel case enclosing a bundle of optical fibers extending between a distal end (tip end) and proximal end of the endoscope for transmitting light through the endoscope. A fiber optic cable delivers light from a light source into the case through an aperture situated near the proximal end of the endoscope. The optical fibers transmit the light through to the distal end, where the light exits the endoscope and illuminates the area near the distal end. The endoscope in turn transmits an image of that area through a rod and lens system to an eyepiece lens at the proximal end. A video camera coupled to the eyepiece converts the image into electronic signals and transmits the signals to a video monitor, where the image is displayed. Endoscopes are used most often in "minimally invasive surgery", in which an endoscope is inserted into a patient, allowing a surgeon to illuminate and view the interior of the patient with minimal penetration. The use of endoscopic surgery is growing, in large part because it is generally safer and less expensive than conventional surgery, and patients tend to require less time in a hospital after endoscopic surgery. Conservative industry experts estimate that about 4 million minimally invasive procedures were performed in 1996. As endoscopic surgery becomes more common, there is an increasing need to accurately evaluate the performance characteristics of endoscopes . To obtain a true measure of the performance of an endoscope, both the lens and the optical fibers should be evaluated. For example, some optical fibers may be damaged and only partially transmit light. In addition, the lens may distort images or blur the sharpness of image colors. These and other shortcomings in the optical performance of endoscopes may be the result of imperfections in the manufacturing process and/or may develop as the endoscope is used over time. An apparatus for evaluating the performance characteristics of endoscopes would be able to validate claims made by endoscope vendors about the capabilities of their products. Accordingly, such an apparatus would be advantageous for the purchasers and users of endoscopes. In addition, such an apparatus would be of great use in evaluating disposable endoscopes, which currently have an average life of about 20 to 30 uses. An apparatus for evaluating the performance characteristic of endoscopes would be able to determine when a disposable endoscope is so degraded that it should be discarded. Furthermore, an endoscope may be adequate for one surgical procedure but inadequate for another which requires more precision, such as when a patient is bleeding. Currently, an endoscope which is suspected of having any deficiency must be removed from service and sent for repair, which can be both costly and time consuming. An apparatus for evaluating the performance characteristics of endoscopes would preferably be able to identify endoscopes which are appropriate for one type of procedure although inadequate for another. Such an apparatus would also be most advantageous in a program of preventative endoscope maintenance. Endoscopes cost thousands of dollars, and typically require repairs at least about twice per year which can cost several thousand dollars per repair. There is a need for a tool for evaluating the performance characteristics of endoscopes, thereby verifying if repairs have been effective. An apparatus for evaluating endoscope performance ideally would also be able to store the results of past tests and evaluations, thereby allowing the system to evaluate changes in endoscope performance after repair operations and over the lifetime of the endoscope. In addition, such information on changes in endoscope performance would be useful in predicting changes in the performance of other endoscopes before their performance degrades . This would help predict f ture endoscope needs . The present inventors are not aware of any commercially available tools for use in a clinical environment which quantitatively assess the performance characteristics of endoscopes. A further complication is that endoscopes vary in length, diameter and tip angle, which is the angle between the direction of view and the longitudinal axis of the endoscope. A system for evaluating endoscope performance would ideally also be able to accommodate endoscopes which have varying optical and/or physical characteristics. Accordingly, it is an object of the present invention to provide a method and apparatus for evaluating the optical performance characteristics of fiber optic endoscopes . Summary Of The Invention The present invention is directed to an apparatus and method for performing tests on the fiber optic path and the lens system of an endoscope, and in turn evaluating the optical performance of the endoscope in dependence on the results of the tests . According to the present invention, a beam of light defining a predetermined intensity pattern is transmitted through the endoscope from a first end of the endoscope through a second end, and signals are generated indicative of the optical intensity of the transmitted beam at each of a plurality of predetermined locations within the beam. A second set of signals indicative of one or more performance characteristics of the endoscope are generated in response to the intensity signals and to signals indicative of the test type. Preferably, a plurality of targets are employed to each generate a predetermined intensity pattern defining either a uniform intensity, or an intensity which varies periodically, such as a sinusoidal-varying medium, in a predetermined direction across the transmitted beam. In the preferred embodiment of the invention, the targets are selected to perform each of the following tests: (i) a light loss test, (ii) a reflective symmetry test, (iii) a lighted fibers test, (iv) a geometric distortion test, and (v) a modulation transfer function (MTF) test. A video system generates signals indicative of the optical intensity of the beam after transmission through the endoscope at each of a plurality of predetermined locations within the beam. The video signals are in turn evaluated in accordance with the selected tests in order to provide graphical and numerical indicia of the optical performance characteristics of the endoscope. One advantage of the apparatus and method of the present invention is that both the lens and optical fibers of an endoscope are tested and evaluated in order to accurately and quantitatively assess the performance characteristics of the endoscope. Other advantages of the present invention will become apparent in view of the following detailed description and accompanying drawings . Brief Description Of The Drawings FIG. 1 is a schematic illustration of an apparatus for evaluating the optical performance characteristics of fiber optic endoscopes in accordance with the present invention. FIG. 2 is a perspective view of a test station of the apparatus of FIG. 1 for accommodating endoscopes of differing optical and physical characteristics, such as differing tip angles, lengths and diameters, and with parts removed for clarity. FIG. 3a is a perspective view of the carrier of the test station of FIG. 2 and the associated targets for performing the light loss, reflective symmetry, geometric distortion, lighted fibers and modulation transfer function (MTF) tests on the endoscopes. FIG. 3b is a partial cross-sectional view of the carrier of FIG. 3a illustrating the target for performing the MTF test in further detail. FIG. 4 is a flow chart illustrating conceptually the procedural steps for performing a light loss test on the endoscopes in the apparatus of FIG. 1. FIG. 5 is a flow chart illustrating conceptually the procedural steps for performing a reflective symmetry test on the endoscopes in the apparatus of FIG. 1. FIG. 6 is a flow chart illustrating conceptually the procedural steps for performing a lighted fibers test on the endoscopes in the apparatus of FIG. 1. FIG. 7 is a flow chart illustrating conceptually the procedural steps for performing a geometric distortion test on the endoscopes in the apparatus of FIG. 1. FIG. 8 is a flow chart illustrating conceptually the procedural steps for performing a MTF test on endoscopes in the apparatus of FIG. 1. FIG. 9A is an exemplary graph illustrating the intensity of a light beam generated by the light source of the apparatus of FIG. 1 before transmission through an exemplary endoscope. FIG. 9B is an exemplary graph illustrating the intensity of a light beam generated by the light source of the apparatus of FIG. 1 after transmission through an exemplary endoscope. FIG. 10 is an exemplary display of a graphical user interface provided by a computer of the apparatus of FIG. 1 illustrating a selection of tests that may be performed on an endoscope in accordance with the invention. FIG. 11 is an exemplary display of a graphical user interface provided by the computer of FIG. 1 for evaluating the results of a light loss test. FIG. 12 is an exemplary display of a graphical user interface provided by the computer of FIG. 1 for evaluating the results of a reflective symmetry test. FIG. 13 is another exemplary display of a graphical user interface provided by the computer of FIG. 1 for evaluating the results of a reflective symmetry test. FIG. 14 is another exemplary display of a graphical user interface provided by the computer of FIG. 1 for evaluating the results of a reflective symmetry test. FIG. 15a is an exemplary display of a graphical user interface provided by the computer of FIG. 1 for evaluating the results of a lighted fibers test. FIG. 15b is another exemplary display of a graphical user interface provided by the computer of FIG. 1 for evaluating the results of a lighted fibers test. FIG. 16 is another exemplary display of a graphical user interface provided by the computer of FIG. 1 for evaluating the results of a lighted fibers test. FIG. 17 is an exemplary display of a graphical user interface provided by the computer of FIG. 1 for evaluating the results of a geometric distortion test. FIG. 18 is another exemplary display of a graphical user interface provided by the computer of FIG. 1 for evaluating the results of a geometric distortion test. FIG. 19 is an exemplary display of a graphical user interface provided by the computer of FIG. 1 for evaluating the results of an MTF test. FIG. 20 is another exemplary display of a graphical user interface provided by the computer of FIG. 1 for evaluating the results of an MTF test. FIG. 21 is an exemplary graph illustrating the definition of modulation at a location within an image transmitted through an endoscope. FIG. 22 is a schematic illustration of the distal end of an exemplary endoscope spaced apart from a semi- transparent medium for purposes of performing the MTF test in the apparatus of FIG. 1 in accordance with the present invention. FIG. 23a is an exemplary, schematic illustration of the relative orientation between a semi-transparent medium used to perform the MTF test in accordance with the present invention and a scan direction parallel to the direction of variation in the transmittance of the medium. FIG. 23b is an exemplary, schematic illustration of another semi-transparent medium used to perform the MTF test in accordance with the present invention and having an orientation relative to the scan direction different than the orientation of FIG. 23a. FIG. 24 is an exemplary graph illustrating in simplified form the attenuation characteristics of a low- pass filter. FIG. 25 is a side elevational view of the carrier of the test station of FIG. 2, taken from the right side. FIG. 26A is a partly in section side elevational view of the mounting arm coupled to the arm support of the test station of FIG. 2, taken from the left side. FIG. 26B is a partly in section front elevational view of the mounting arm of the test station of FIG. 2. FIG. 26C is a front elevational view of an alternate embodiment of the mounting arm of the test station of FIG. 2. Detailed Description Of The Preferred Embodiment The preferred embodiment of the present invention is embodied in a low-cost endoscope evaluation system which accommodates endoscopes of different tip angles, lengths and diameters, performs tests on the endoscopes, and in turn evaluates the optical performance of the endoscopes in dependence on the results of the tests . The preferred embodiment of the invention furthermore performs a selection of tests which evaluate the optical performance of both the optical fibers and lens of an endoscope, and thereby may provide a relatively accurate assessment of the effectiveness of a repair operation performed on an endoscope, as well as determine and record changes in the optical performance characteristics of an endoscope over its lifetime. In FIG. 1, an apparatus embodying the present invention for performing tests on endoscopes and for evaluating the optical performance of the endoscopes in dependence on the results of the tests is indicated generally by the reference numeral 10. The apparatus 10 comprises a test station 12 including an adjustable mounting arm 14 for receiving and retaining an endoscope to be tested, and a carrier 16 for positioning a selected target under the distal end (tip) of the endoscope for performing a respective test. A variable, high-intensity light source 18, such as a xenon arc lamp or a halogen bulb, delivers light along a fiber optic cable 20 which is detachably connected to the endoscope through an aperture situated near its proximal end. In the currently preferred embodiment, the light source 18 is a variable xenon short-arc lamp, such as the 150 watt lamp sold under model no. 610 by Karl Storz Endoscopy-America Inc. of Culver City, CA. As is described further below, during certain tests the fiber optic cable 20 is detached from the endoscope and re-positioned to directly illuminate a target on the carrier 16. The test station 12 and the position of the fiber optic cable 20 during each of the tests performed on a typical endoscope are described in detail below. A video system 22 generates signals indicative of the image which is projected through the eyepiece at the proximal end of the endoscope. In the preferred embodiment, the video system 22 comprises a charge-coupled device (CCD) video camera 24 coupled to the eyepiece and a video signal processor 26 coupled to the camera. As is known in the art, the CCD video camera records an image by storing charges in a plurality of semiconductor potential wells, thereby defining a two-dimensional array of charges which each correspond to the intensity at a point in the transmitted image. The video signal processor 26 transfers the charges out of the wells and thereby generates time-varying video signals indicative of the recorded image. The CCD video camera 24 is coupled to the endoscope eyepiece with an adjustable vice 28 having a lens system with both zoom and focus control rings. Thus, the projected image may be properly zoomed and focused through the vice lens system 28 before it is recorded by the camera 24. The video system 22 transmits the signals indicative of the image through a BNC connector to a standard video monitor 30 which displays the image, and to a desktop computer 32 which processes the signals in accordance with the present invention, as is described further below. In the currently-preferred embodiment, the computer 32 is an Intel Pentium™ microprocessor-based desktop computer which includes known computer software and peripheral devices as is necessary for its operation, such as an operating system, a keyboard, a hard disk, random access memory (RAM), a computer monitor and a mouse. The computer 32 further includes a frame grabber card (not shown) , which is an analog-to-digital converter for receiving the image signals from the video system 22 and generating in dependence thereon digital signals indicative of the image. The frame grabber card thus translates the image signals from the format of the video system 22 to a digital format which the computer's microprocessor can accept and manipulate. The digital signals generated by the frame grabber card are preferably in the format of a 512 by 512 array of pixel intensities, and thus the number of pixels generated by the card is approximately determined as follows: 512 x 512 = 262,144 pixels. The frame grabber card is preferably a "plug-in card" which is detachably connected to the system bus of the computer 32 in a known manner. The frame grabber card may be implemented with an "RT Mono"™ video capture board, sold by Digital Vision, Inc. of Dedham, MA, and driver software sold by Viewpoint Solutions of Rochester, NY for providing an interface between the video capture board and the standard Pentium™-based computer. Alternatively, the frame grabber card may be implemented with an IMAC PCI-1408 video capture board, sold by National Instruments of Austin, TX. IMAQ Vision software and NI-IMAQ driver software, also sold by National Instruments, may provide the interface between the IMAC PCI-1408 video capture board and the standard Pentium™-based desktop computer. The computer 32 is coupled in a known manner to a standard printer 34 for printing images processed by the computer. In the preferred embodiment, the printer 34 is a laser printer having a resolution of at least about 600 dots per inch (dpi) . Turning to FIG. 2, the test station 12 comprises a frame 36 including an upstanding arm support 38, and a carrier support 40 defining a horizontal support surface. As indicated by the arrows in FIG. 2, the mounting arm 14 is pivotally coupled to the arm support 38 and the angular position of the arm is adjustable relative to the carrier support 40 in order to accommodate endoscopes of all possible tip angles. In the preferred embodiment, the mounting arm 14 accepts endoscopes having outer diameters within the range of approximately 1.9 through 10.0 millimeters, lengths within range of approximately 4 inches through 13 inches, and tip angles within the range of approximately 0 degrees through 120 degrees. As shown in FIG. 2, the carrier 16 is mounted on the carrier support 40 adjacent to the mounting arm 14 and is moveable relative to the mounting arm along rails 31 in order to adjust the position of the carrier relative to an endoscope on the mounting arm. As is described further below, the carrier 16 includes a plurality of targets, each for performing a respective test to evaluate the optical performance of the endoscopes. The carrier support 40 defines an aperture 42 extending through the support surface immediately below the base of the mounting arm. In the preferred embodiment of the test station, the aperture 42 is approximately circular and defines a diameter of approximately 1.9 inches . As shown schematically in FIG. 1, directly beneath the aperture 42 and fixed to the underside of the carrier support 40 is a fiber optic cable holder 44 of a type known to those of ordinary skill in the pertinent art. The cable holder 44 receives and retains the fiber optic cable 20 in order to transmit a beam of light from the light source 18 through the aperture 42 to the distal end or tip of an endoscope being tested. A collimating lens 46 is fixed to the underside of the carrier support 40 and covers the aperture 42 in order to collimate the light beam projected through the aperture . As illustrated in FIG. 3a, in the preferred embodiment there are four targets mounted on the carrier 16, each of which is used in at least one of five tests for evaluating the performance of the endoscope and described in detail below. The term "target" is used herein to broadly describe any of the various devices used for receiving and/or reflecting a transmitted beam as part of each of the tests for evaluating the performance characteristics of the endoscopes, as described further below. The first target 47 is a photometer sensor which is coupled to a photometer 50 for measuring the intensity of light received by the sensor. A fixture 52 including a base 54 and three upstanding legs 56 is removably mounted above the photometer sensor 47 for detachably connecting the fiber optic cable 20 to the base in order to illuminate the sensor. The upstanding legs 56 define a predetermined length so that the distance between the base 54 and the sensor 50, and thus the distance between the end of the fiber optic cable 20 and the sensor, is approximately equal to the distance between the photometer sensor and the distal end of an endoscope supported on the mounting arm. In the currently-preferred embodiment, this predetermined distance is approximately two inches. The second target 58, which is used in two tests in the preferred embodiment, defines a nonspecular reflective surface 60, such as a Kodak R27, 90% reflectance card or a white sheet of paper. As is known in the art, a nonspecular reflective surface like the surface 60 is one which does not form a mirror-like reflected image, but rather diffuses the reflected light. A transparent film 62 having a printed reference pattern 63 is overlaid on the reflective surface 60 during at least one test. The reference pattern 63 printed on the transparent film 62 defines a number of reference points having a predetermined separation distance. As shown is FIG. 3a, the reference pattern is preferably a black, rectangular grid defining two sets of parallel lines spaced approximately 0.2 inches apart, wherein each of the first set of lines is perpendicular to each of the second set of lines. The reference pattern thus defines a set of squares having approximately 0.2 inch sides. The third target 64 defines a substantially mirror-like surface 65, and is preferably a circular reflector plate formed of a material having a reflectance preferably within the range of approximately 5% and approximately 40% reflectance, such as Lucite™, which is laid over a black background to provide the mirror-like quality. The surface 65 thus creates a specular (mirrorlike) reflection. The reflectance of the surface 65 is selected to minimize the reflection of incident light, and thereby maintain the intensity of the light reflected back through any damaged fibers below a predetermined intensity level. As is described below, damaged fibers may be identified by their inability to transmit light having an intensity below a predetermined level. The substantially mirror-like surface 65 rests on three adjustable legs 63, allowing precise control over the separation between the endoscope tip and the reflective surface. The fourth target is a semi-transparent medium 48, such as a film, and defines a transmittance which varies periodically along a predetermined direction within the medium. A beam of light which is filtered through the semi- transparent medium 48 will therefore have an intensity which varies periodically along the predetermined direction within the beam. In the preferred embodiment, the semi-transparent medium 48 has a transmittance which varies sinusoidally along the semi-transparent medium in a first direction, and which is substantially constant along the medium in a second direction transverse to the first direction. Also in the preferred embodiment, the sinusoidally-varying transmittance of the medium defines a spatial frequency of one cycle per millimeter (cycles per unit length) , and is preferably of the type sold by Sine Patterns, Inc. of Penfield, NY. As shown in FIG. 3b, an approximately circular aperture 49 is formed through the carrier 16, a diffusing opal glass plate 55 is superimposed over the aperture, a white plastic translucent sheet 57 is superimposed over the glass plate, and the semi-transparent medium 48 is seated over the plastic sheet. As is described further below, when performing the MTF test the carrier 16 is positioned to align the circular aperture 49 with the aperture 42 of the carrier support 40, and the free end of the fiber optic cable 20 is mounted beneath the aperture 42 to transmit a beam through the apertures, and in turn through the glass plate 55, white plastic sheet 57 and semi-transparent medium 48. The glass plate 55 and plastic sheet 57 together diffuse the beam from the fiber optic cable, creating a beam of substantially uniform intensity, and the semi-transparent medium 48 in turn filters the substantially uniform intensity beam to generate a beam which varies approximately sinusoidally along the first direction. A black paper mask 59 defining a plurality of apertures is preferably inserted between the semi- transparent medium 48 and the white plastic sheet 57 in order to block light transmission through portions of the medium, and thereby enhance selected points in an image corresponding to the non-masked (illuminated) portions of the medium. As is described further below, each aperture of the black paper mask 59 defines a respective portion of the transmitted beam image within which the MTF is measured. TEST PERFORMANCE As indicated above, the following five tests are preferably performed with the apparatus of the invention in order to evaluate both the optical fibers and lens system of an endoscope: (i) light loss test, (ii) reflective symmetry test, (iii) lighted fibers test, (iv) geometric distortion test, and (v) MTF test. The details of each test, along with the preferred methods for analyzing the results of these tests to thereby evaluate the performance characteristics of the endoscopes, are hereinafter described. FIG. 4 illustrates a flow chart 66 for performing the first test (light loss test) which is directed to measuring the reduction in the intensity of light after transmission through an endoscope. In general, the test comprises measuring two quantities: the intensity of light which exits the fiber optic cable ("light in") and the intensity of light which exits the fiber optic cable and is transmitted through the endoscope ("light out") . In performing the light loss test, the light source 18 (FIG. 1) is activated (step 68), set to a selected intensity level, and preferably left active for a predetermined period of time in order to allow the light source to reach the selected intensity level. In the preferred embodiment, the predetermined intensity level is determined such that the intensity of light transmitted through the endoscope is within the preferred operating range of the photometer sensor target 54, and the predetermined period of time is at least approximately ten minutes. The free end of the fiber optic cable 20 (FIG. 1) is then coupled to the fixture 52 (FIG. 3a) and thereby spaced a predetermined distance above the photometer sensor target 54 (which is approximately equal to the distance between the tip end of the selected endoscope supported on the mounting arm and the target) to thereby illuminate the sensor (step 70) . The photometer intensity reading is then recorded and designated "light in" (step 72) . After the "light in" intensity is recorded, the cable 20 is removed from the carrier fixture 52 (FIG. 3a) and attached to the proximal end of the endoscope supported on the mounting arm 14 (step 74), as indicated in FIG. 1. The angular position of the mounting arm 14 is adjusted relative to the photometer sensor target 54 to correspond to the actual tip angle of the endoscope tested. The position of the carrier 16 is also adjusted so that the photometer sensor target 54 is positioned directly underneath, or aligned with the endoscope tip and spaced the predetermined distance (approximately two inches) from the endoscope tip (step 76) . In the final step of the light loss test, the photometer intensity reading is recorded (step 78) , and this intensity reading is designated the "light out". Both the "light in" and "light out" readings are recorded and used, as described below, in measuring the reduction in the intensity of light after transmission through the endoscope. FIG. 5 illustrates a flow chart 80 for performing the second test (reflective symmetry test) which is directed to measuring the reflective symmetry of light which exits the eyepiece of the endoscope. When an ideal endoscope transmits an image of uniform intensity from its tip end to its proximal end, the transmitted image is approximately circularly symmetrical about the center of the transmitted image. Thus, the intensity in the center of the transmitted image is greatest, and the intensity decreases at locations in the transmitted image spaced radially from the center. All points which are equally distant from the center of the transmitted image have approximately equal intensities, and the intensity at the periphery of the transmitted image is lowest. In actual (non-ideal) endoscopes, deviation from the circular symmetry of the transmitted image indicates damaged optical fibers . In performing the reflective symmetry test, the light source 18 (FIG. 1) is activated (step 82) and set to a selected intensity level. In the preferred embodiment, the predetermined intensity level is determined such that the intensity of light transmitted through the endoscope is within the preferred operating range of the video system 22 (Fig. 1) . The fiber optic cable 20 (FIG. 1) is attached to the endoscope supported on the mounting arm (step 84) , and the carrier is positioned so that the second target, the reflective surface 65, is positioned directly underneath, or aligned with the endoscope tip (step 86) . The video system 22 is then focused on the reflective surface 65 (step 88) . A preferred method for focusing the video system is to overlay a reference pattern film, such as the transparent film 62 (FIG. 3a), on the reflective surface 65, set the adjustable vice 28 connecting the video system 22 (FIG. 1) to the endoscope to its maximum zoom setting, and then adjust the focus ring of the vice to bring the reference pattern into focus. Once the video system 22 is focused, the reference pattern film 62 is removed from the reflective surface 65. As discussed above, the center of the transmitted image should have the highest intensity. However, if the endoscope is not oriented properly (i.e. if the tip angle is not substantially equal to the angle of the mounting arm) , the point of highest intensity in the transmitted image will not coincide with the center of the transmitted image. Accordingly, if necessary, the angular position of the mounting arm must be adjusted until the approximate center of the transmitted image has the highest intensity (step 90). Unfortunately, endoscope tip angles are generally not held to a tight tolerance, and thus the proper angle of the mounting arm generally cannot be set based only on the purported (nominal) tip angle of the endoscope. A preferred method for orienting the endoscope is to adjust the angle of the mounting arm 14 while the video system 22 displays the transmitted image on the video monitor 30 (FIG. 1) or on a computer monitor of the computer system 32 (FIG. 1) . In this manner, a human operator can adjust the mounting arm 14 by viewing the transmitted image on the monitor and simultaneously moving the arm until the center of the transmitted image coincides with the point of highest intensity. Once the endoscope is properly oriented, the frame grabber card stores the transmitted image and generates digital signals indicative of the image (step 92) . It is preferable that the frame grabber card have an adjustable range of intensities which it can accept and translate to digital format. It is most preferable that in each test the frame grabber card generates signals indicative of white pixels for the highest intensities in the stored image, and signals indicative of black pixels for the lowest intensities in the stored image. In this manner, the frame grabber card produces pixels having intensities which span approximately the entire output range of the card, which in turn improves resolution and facilitates evaluation of the test results. The computer system 32 processes the digital signals (pixels) when evaluating the endoscope, as described further below. FIG. 6 illustrates a flow chart 100 for performing the third test (lighted fibers test) which is directed to measuring the ability of the endoscope optical fibers to transmit low-intensity light. The light source 18 (FIG. 1) is activated (step 102) and set to a selected intensity level. In the preferred embodiment, the predetermined intensity level is determined such that the intensity of light transmitted through the endoscope is within the preferred operating range of the video system 22 (Fig. 1) . The fiber optic cable 20 (FIG. 1) is attached to the proximal end of the endoscope supported on the mounting arm (step 104) , and the carrier is positioned so that the third target defining the substantially mirror-like surface 65 is positioned directly underneath, or aligned with the endoscope tip at a relatively close distance selected to produce a focused, specular reflection of the lighted optical fibers at the endoscope eyepiece (step 106). This distance is typically less than approximately 0.25 inches. The frame grabber card stores the transmitted image and generates digital signals indicative of the image (step 108) which the computer 32 processes when evaluating the image data. FIG. 7 illustrates a flow chart 110 for performing the fourth test (geometric distortion test) which is directed to measuring the degree to which the endoscope geometrically distorts an image. Distortion at a point in the transmitted image is defined as the ratio of the magnification at that point to the magnification at the center of the transmitted image. A preferred method for measuring distortion is to transmit through the endoscope an image of a plurality of equally-sized squares, and to then measure and compare the diagonal lengths of the corresponding squares in the transmitted image. The light source 18 (FIG. 1) is activated (step 112) and set to a selected intensity level. In the preferred embodiment, the predetermined intensity level is determined such that the intensity of light transmitted through the endoscope is within the preferred operating range of the video system 22 (Fig. 1) . The fiber optic cable 20 (FIG. 1) is attached to the proximal end of the endoscope supported on the mounting arm (step 114) , and the carrier is positioned so that the second target 58 defining the reflective surface 60 is positioned directly underneath, or aligned with the endoscope tip (step 116) . In addition, the transparent film 62 with the reference pattern 63 is overlaid on the reflective surface 60 and the video system 22 is then focused on the pattern (step 118) . A preferred method of focusing the video system 22 is to set the adjustable vice to maximum zoom, and to then adjust the focus ring of the vice to bring the reference pattern into focus. Once the video system 22 is focused, the frame grabber card stores the transmitted image and generates digital signals indicative of the image (step 120) . The computer 32 processes the digital signals when evaluating the endoscope, as is described further below. FIG. 8 illustrates a flow chart 130 for performing the fifth test (MTF test) which is directed to measuring the modulation transfer function (MTF) of the endoscope at a predetermined spatial frequency, which is equivalent to measuring the modulation transfer ratio (MTR) of the endoscope while it transmits an image having an intensity which varies along a direction at the predetermined spatial frequency. An image's modulation is correlated with the contrast (sharpness) of the image. The modulation at a location in an image is defined by the maximum intensity and the minimum intensity at that location as follows: modulation = (maximum intensity - minimum intensity) ÷ (maximum intensity + minimum intensity) As used herein, the terms "maximum intensity" and "minimum intensity" refer to the local maxima and minima, respectively, of a cycle in the periodically-varying intensity. An endoscope reduces the modulation of a transmitted image, so that the transmitted image is not as sharp as the image received at the endoscope tip. The MTR is a measure of the change in an image's modulation after transmission through the endoscope. The MTR is defined as follows : MTR = modulation of image after transmission ÷ modulation of image before transmission FIGS. 9A and 9B illustrate the maximum and minimum intensities in an image before and after transmission through an endoscope, respectively. The graph 140 in FIG. 9A represents the sinusoidally-varying intensity of an image which is received at the endoscope tip (i.e. before transmission through the endoscope) . Points 146 and 150 have a maximal intensity 142, while a point 148 has a minimal intensity 144. The intensity variation 143 in the image before transmission is the difference between the maximal intensity 142 and the minimal intensity 144. The graph 160 in FIG. 9B represents the sinusoidally-varying intensity of an image after transmission through the endoscope. Points 166 and 170 have a maximal intensity 162, while a point 168 has a minimal intensity 164. The points 166, 168 and 170 of the transmitted image (FIG. 9B) correspond respectively to the points 146, 148 and 150 of the received image (FIG. 9A) . The intensity variation 163 in the image after transmission is the difference between the maximal intensity 162 and the minimal intensity 164. The intensity variation 163 in the image after transmission is less than the intensity variation 143 in the image before transmission. In other words, transmission through the endoscope reduces the sharpness of the image. The MTF test is directed to measuring this reduction in sharpness at different locations in the transmitted image. Referring again to FIG. 8, in performing the MTF test, the light source 18 (FIG. 1) is activated (step 132) and set to a selected intensity level. In the preferred embodiment, the predetermined intensity level is determined such that the intensity of light transmitted through the endoscope is within the preferred operating range of the video system 22 (Fig. 1) . The free end of the fiber optic cable 20 (FIG. 1) is attached to the fiber optic cable holder 44 (FIG. 1) mounted below the aperture 42 of the carrier support 40 (step 134) , in order to transmit a light beam through the aperture. The carrier 16 is then positioned so that the fourth target, the semi-transparent medium 48, is positioned directly underneath the endoscope tip and above the carrier support aperture 42 (step 136) , thereby filtering the beam projected from the fiber optic cable and transmitting the filtered beam through the endoscope. The frame grabber card stores the transmitted image and generates digital signals indicative of the image (step 138) . In summary, each of the tests described above are preferably performed on each endoscope in order to provide test results comprising a set of signals indicative of intensities at predetermined locations in a beam of light transmitted through the endoscope. As hereinafter described, the system of the invention preferably further generates a second set of signals responsive to the test result signals and which is indicative of the performance characteristics of the endoscope. The manner in which the second set of signals is generated depends on the particular test used to generate the corresponding test result signals. TEST RESULT EVALUATION For each of the above-described tests, the computer system 32 (FIG. 1) receives the signals indicative of the beam intensities, and generates the second set of signals in accordance with the intensity signals and further in accordance with signals indicative of the test type. FIG. 10 shows an exemplary display 180 of a graphical user interface (GUI) generated and displayed on the monitor of the computer system 32. As is known in the art, a GUI provides both a means for user input and a means for the computer system to display information. The GUI provides signals indicative of the type of test, typically in accordance with user commands such as the actuation of graphical buttons and switches. In the preferred ® embodiment, the GUI is implemented using LabVIEW software sold by National Instruments of Austin, TX. Accordingly, the various types of displays and input methods of the GUI described herein are those which are most easily implemented ® with LabVIEW software. However, those skilled the art will recognize that other types displays and input methods may be implemented, including other forms of graphical, textual and audio input and output. The display 180 includes graphical "buttons" which the user actuates via mouse or keyboard actions in a manner known in the art. Upon actuation of a button 182, the GUI provides a second display (not shown) into which the user may enter information related to the endoscope being tested. Such information includes the endoscope identification code, manufacturer, diameter, length and tip angle, as well as any reported and observed problems with the endoscope. Further types of information may be included without departing from the scope of the present invention. A graphical indicator 186 displays a message which indicates whether the endoscope supported on the mounting arm is untested, has passed a test, or has failed a test. Actuation of a button 187 signals that a new endoscope is to be evaluated, and that previously stored test results are therefore inapplicable to this endoscope. Accordingly, upon actuation of the button 187, the graphical indicator 186 displays a message indicating that the endoscope is untested. Actuation of a button 184 provides a third display 200 shown in FIG. 11. The display 200 facilitates analysis of the results of the light loss test. As described above, performing the light loss test yields signals indicative of a Light-In and a Light-Out measurement from the photometer sensor 47. The ratio of these two intensities yields the light loss of the tested endoscope in units of Optical decibels (dB Optical) in accordance with the following relationship : Light Loss = 10 log (Light-Out / Light-In) The user provides the Light-In reading in a text entry region 202 and the Light-Out reading in another text entry region 204. Upon entry of valid numerical values in both text entry regions 202 and 204, the computer system 32 generates signals indicative of the entered readings, and in turn generates signals indicative of the Light Loss in accordance with the above relationship. Finally, the computer system 32 displays a textual indication of the Light Loss in a display region 206. The displayed Light Loss allows the user to compare the endoscope under test with average or expected Light Loss values, which generally depend on the diameter of the endoscope. Typical values for Light Loss are about (- 6 ± 3 ) dB Optical for a 10 millimeter diameter endoscope, and about (- 16 + 3) dB Optical for endoscopes with diameters between 2 and 4 millimeters. Referring again to FIG. 10, actuation of the buttons 188, 190, 192 and 194 initiates analyses of the results of the reflective symmetry test, MTF test, lighted fibers test and geometric distortion test, respectively. The analyses of the results of these four tests are directed generally to generating signals which are indicative of the degree to which the tested endoscope attenuates the intensity of the transmitted beam at predetermined locations within the beam. Actuation of the button 188 initiates analysis of the results of the reflective symmetry test, and causes the GUI to provide a display of the type indicated by the reference numeral 210 of FIG. 12. The display 210 includes a region 212 showing a graphical display of an intensity pattern of the transmitted beam. In the preferred embodiment, the region 212 defines a two-dimensional array of pixels, and each pixel has a color (e.g., a shade of gray) indicating the intensity of the transmitted beam at a location in the beam corresponding to the location of the pixel. Also in the preferred embodiment, a substantially white pixel indicates a location in the beam with the highest intensity relative to all pixels, while a substantially black pixel indicates a location in the beam with the lowest intensity relative to all pixels. As shown in FIG. 12, the region 212 defines a plurality of concentric regions, each defining a respective intensity range and corresponding to a respective region within the transmitted beam. In the preferred embodiment, the intensity of a respective concentric region is indicated by the shade of that region. The lighter the shade, the higher is the intensity of the region; and the darker the shade, the lower is the intensity of the region. Referring to the exemplary graphical image shown in the region 212 of FIG. 12, the region 212 defines an approximately oval central region 230, three approximately concentric annular regions 232, 234 and 236 progressively spaced outwardly from the central region in the radial direction, and a peripheral region 238 surrounding the outermost annular region 236. The central region 230 contains pixels which are white, and thus defines the region within the beam of highest intensity. Typically, the pixels spaced radially outwardly from the central region 230 define progressively darker shades, and the pixels at the peripheral region 238 of the display are substantially black because they correspond to the periphery of the transmitted beam defining the lowest intensity. Although the exemplary graphical image shown in the region 212 defines five regions 230, 232, 234, 236 and 238, and thus the region 212 indicates five intensity ranges, those skilled in the art will recognize that a number of intensity ranges different than the five shown may be used without departing from the scope of the invention. The region 212 further includes a vertical indicator bar 226 and a horizontal indicator bar 228 which may be moved horizontally and vertically, respectively, within the region 212 by appropriate user command (e.g. a mouse action or keyboard key press) . Each bar 226 and 228 defines a plurality of collinear pixels in the display and, thus, corresponds to a plurality of approximately collinear locations within the transmitted beam. The display 210 further includes a vertical cross- section display region 216 showing a graphical display indicative of the intensity of the transmitted beam in the approximately collinear locations defined by the vertical bar 226 of the region 212. The intensity curve shown in the region 216 is formed by a plurality of pixels each having a vertical position corresponding to the vertical position of a pixel in the region 212 along the vertical bar 226, and a horizontal position corresponding to the intensity of that pixel . Similarly, the display 210 further includes a horizontal cross-section display region 214 showing a graphical display indicative of the intensity of the transmitted beam in the approximately collinear locations defined by the horizontal bar 228 of the region 212. The intensity curve shown is formed by a plurality of pixels each having a horizontal position corresponding to the horizontal position of a pixel in the region 212 along the horizontal bar 228, and a vertical position corresponding to the intensity of that pixel. Upon actuation of a button 222 on the display 210, a display 250 of the type shown in FIG. 13 is generated which includes a display region 252 comprising a three- dimensional image indicative of the intensity of the transmitted beam and corresponding to the image of the region 212 (FIG. 12) . A region 254 includes controls for adjusting the point-of-view of the three-dimensional image, and a region 256 includes controls for adjusting the scale of the three-dimensional image along three mutually- perpendicular directions (e.g., the x, y and z coordinate directions) . The three regions 212, 214 and 216 (FIG. 12) and the three-dimensional image (FIG. 13) each provide an indication of the degree to which the transmitted image is circularly symmetrical, and thus the degree to which the intensity of the transmitted beam is symmetrical (or non- symmetrical) about its center. A user may be able to evaluate an endoscope based on this type of graphical feedback alone, and determine whether or not the endoscope is acceptable. However, as discussed below, the computer system 32 of the invention further provides an explicit indication of whether the tested endoscope passes a threshold standard for the reflective symmetry test. Referring again to FIG. 12, upon actuation of a button 224 on the display 210, a display 268 of the type shown in FIG. 14 is generated. The display 268 indicates, for each of a plurality of intensity ranges, the number of pixels which correspond to that intensity. The display 268 includes a region 262 showing a histogram comprising a plurality of vertical bars. A region 260 comprising a plurality of text entry areas allows the user to define each intensity range by entering values defining the upper bounds of the intensity ranges. A region 258 provides a plurality of numerical values corresponding to the number of pixels included in each intensity range. And a region 265 provides a plurality of numerical values corresponding to the percentage of pixels included in each intensity range. Accordingly, the regions 258, 262 and 265 display substantially the same information in three different formats. A selector 264 is set by the user to select one of the intensity ranges. A textual display 266 indicates the percentage of pixels having an intensity within or above the range indicated by the selector 264. For example, if the selector 264 is set to the second highest intensity range, the textual display 266 will indicate the percentage of pixels having an intensity included in either the second highest or highest intensity range. A textual display 267 indicates whether the endoscope has passed the reflective symmetry test. A textual display 220 in FIG. 12 also indicates whether the endoscope has passed the reflective symmetry test. In accordance with the invention, an endoscope passes the reflective symmetry test if more than a predetermined percentage of pixels have an intensity greater than a predetermined or threshold intensity level . In the preferred embodiment, the predetermined percentage of pixels is approximately 30%, and the predetermined intensity is approximately 50% of the maximum possible pixel intensity, although these values may be changed using the display 268 as described above (FIG. 14) . As discussed above, the intensity of a pixel corresponds to an intensity of a location in the transmitted beam, which itself is defined by the degree to which the endoscope attenuates the intensity at that location. Thus, it is equivalent to say that an endoscope passes the reflective symmetry test if more than a predetermined number of locations in the transmitted beam have been attenuated by less than a predetermined attenuation. Referring again to FIG. 10, actuation of the button 192 initiates the analysis of the results of the lighted fibers test, and a display 270 of the type shown in FIG. 15a is generated. The display 270 is substantially similar to the display 210 of FIG. 12 for analyzing the results of the reflective symmetry test. The display 270 includes a region 272 showing a graphical display indicative of the intensity of the transmitted beam. The region 272 further includes a vertical indicator bar 286 and a horizontal indicator bar 288. As discussed above with reference to the display 210 of FIG. 12, the bars 286 and 288 each define a plurality of collinear pixels in the display and, therefore, a plurality of substantially collinear locations in the transmitted beam. The display 270 further includes a horizontal cross-section display region 274 corresponding to the horizontal bar 288 of the region 272 and showing the beam intensity at each point within the region 274 along the horizontal bar, and a vertical cross-section display region 276 corresponding to the vertical bar 286 of the region 272 and showing the beam intensity at each point within the region 276 along the vertical bar. Upon actuation of a button 280 on the display 270, a display 290 of the type shown in FIG. 15b is generated which includes a display region 292 comprising a three- dimensional image indicative of the intensity pattern of the transmitted beam and corresponding to the image of the region 272 (Fig. 15a) . A region 294 includes controls for adjusting the point-of-view of the three-dimensional image, and a region 296 includes controls for adjusting the scale of the three-dimensional image along three mutually- perpendicular directions (e.g., the x, y and z coordinate directions) . The three-dimensional image 292 and the three display regions 272, 274 and 276 each provide an indication of the degree to which optical fibers in the endoscope are damaged and do not transmit light. A user may be able to evaluate the endoscope based on this type of graphical feedback alone, and determine whether or not the endoscope is acceptable. However, as discussed below, the computer system 32 of the present invention further provides an explicit indication of whether an endoscope being tested has passed the lighted fibers test. Upon actuation of a button 282 in the display 270, the GUI provides a display 296 of the type shown in FIG. 16. The display 296 includes regions 306 and 308 which indicate, for each of a plurality of intensity ranges, the number of pixels which correspond to the respective intensity range. In the preferred embodiment, only two ranges are considered: intensities above a predetermined intensity ("on") and intensities equal to or below a predetermined intensity ("off") . The display 296 includes a selector 304 with which the user sets the predetermined intensity. The display 296 also includes a selector 302 with which the user selects a value corresponding to a minimum threshold number of pixels. Another selector 300 allows the user to select a range around the selected minimum threshold number of pixels. If the actual number of pixels which are "on" is within this selected range, the endoscope is considered to have passed the lighted fibers test, and the computer system generates signals accordingly. A textual display 298 indicates whether the results of the lighted fibers test indicate that the endoscope has passed. The display 270 (FIG. 15A) also includes a textual display 278 which indicates whether the results of the lighted fibers test indicate that the endoscope has passed. As discussed above, the intensity of a pixel corresponds to an intensity of a location in the transmitted beam. The number of working fibers in the endoscope, which is correlated with the number of white pixels in the display region 272 (FIG. 15A) , depends on such factors as the endoscope 's dimensions, the tip angle and the number of damaged optical fibers. As is also discussed above, the beam intensity at each location is defined by the amount which the endoscope attenuates the intensity at that location. Thus, it is equivalent to say that an endoscope has passed the lighted fibers test if more than a predetermined number of locations in the transmitted beam have been attenuated by less than a predetermined attenuation. In the preferred embodiment described above, the predetermined intensity, the minimum threshold number of pixels, and the range around the selected minimum threshold number of pixels have been described as values which the user may select. However, those skilled in the art will recognize that such values may be fixed and not alterable by the user. Such an embodiment may be preferable if necessary to prevent the user from altering values which define preferred threshold values, or the preferred range for such values . Referring again to FIG. 10, actuation of the button 194 initiates analysis of the results of the geometric distortion test, and causes the GUI to provide the display 310 of the type shown in FIG. 17. The display 310 is substantially similar to the display 210 of FIG. 12 for analyzing the results of the reflective symmetry test, and includes a region 312 showing a graphical display indicative of an intensity pattern of the transmitted beam. The region 312 further includes a vertical indicator bar 320 and a horizontal indicator bar 318 which may be moved horizontally and vertically, respectively, within the region 312 by appropriate user command. As discussed above with reference to the display 210 of FIG. 12, each of the bars 318 and 320 define a plurality of approximately collinear pixels in the display and, therefore, a plurality of substantially collinear locations in the transmitted beam. The display 310 further includes a horizontal cross-section display region 314 corresponding to the horizontal bar 318 of the region 312 and showing the beam intensity at each point within the region 314 along the horizontal bar, and a vertical cross-section display region 316 corresponding to the vertical bar 320 of the region 312 and showing the beam intensity at each point within the region 316 along the vertical bar. Upon actuation of a button 322 on the display 310, a display is generated (not shown) which includes a display region comprising a three-dimensional image indicative of the intensity pattern of the transmitted beam and corresponding to the image of the region 312 (Fig. 17) . Like the displays of FIGS. 13 and 15b, the display includes a region defining controls for adjusting the point-of-view of the three-dimensional image, and another region defining controls for adjusting the scale of the three-dimensional image along three mutually-perpendicular directions (e.g., the x, y and z coordinate directions) . The three-dimensional image and the three regions 312, 314 and 316 each provide an indication of the degree to which the endoscope geometrically distorts the image at different locations in the transmitted beam. A user may be able to evaluate the endoscope based on this type of graphical feedback alone, and determine whether or not the endoscope is acceptable. However, as discussed below, the computer system 32 of the present invention further provides an explicit indication of whether an endoscope being tested has passed the geometric distortion test. Upon actuation of a button 324 in the display 310, the GUI provides a display 330 of the type shown in FIG. 18. The display 330 includes indicators 332, 334, 336, 338 and 340 which each indicate the degree of geometric distortion at a respective location within the transmitted beam. The degree of geometric distortion at each location is determined from the image of the reference pattern forming a part of the transmitted image. As discussed above, the reference pattern 63 (FIG. 3a) defines a set of equally- sized squares, and geometric distortion will cause the reference pattern in the transmitted image to define squares of different sizes or to otherwise distort the shape of one or more squares. Accordingly, the geometric distortion at a location is determined based on the length of the diagonal of the square at that location. In particular, the distortion value at a location is calculated in accordance with the following relationship: Distortion = (Si / S 2 ) - 1 wherein S x = the diagonal length of the square at the respective location; and S 2 = the diagonal length of the central square . Each of the indicators 332, 334, 336, 338 and 340 further indicates whether the results of the distortion calculation at the respective location indicates either a pass or fail condition. In the preferred embodiment, each distortion value is compared to a predetermined distortion threshold. Distortion values which are below the predetermined distortion threshold are considered "fail" values. If at least one of the plurality of distortion values is a fail value, the endoscope will typically fail the geometric distortion test. Textual displays 342 (FIG. 18) and 325 (FIG. 17) indicate whether the endoscope has passed the geometric distortion test. Referring again to FIG. 10, actuation of the button 189 initiates analysis of the results of the MTF test, and causes the GUI to provide a display 350 of the type shown in FIG. 19. The display 350 is substantially similar to the display 210 of FIG. 12 for analyzing the results of the reflective symmetry test. The display 350 includes a region 352 showing a graphical display indicative of the intensity pattern of the transmitted beam, and regions 354 and 356 for displaying cross-sectional views of the display 352 defined by the bars 358 and 360. With reference to the display region 352, the apertures of the black paper mask 59 (FIG. 3b) each define a respective region 359 of the transmitted beam image within which the MTF is measured. In the preferred embodiment, and as shown in FIG. 19, the MTF is measured at the approximate center of the transmitted image, and at select locations on the periphery of the transmitted image, including above center, below center, to the right of center, and to the left of center . A button 362 on the display 350 allows generation of a three-dimensional image (not shown) corresponding to the image of the display 352 and indicative of the intensity pattern of the transmitted beam. The three-dimensional image and the three regions 352, 354 and 356 each provide an indication of the MTF at different locations in the transmitted image. A user may be able to evaluate the endoscope based on this type of graphical feedback alone, and determine whether or not the endoscope is acceptable. However, as discussed below, the computer system 32 of the present invention further provides an explicit indication of whether a tested endoscope has passed the MTF test . Upon actuation of a button 364 in the display 350, the GUI provides a display 370 of the type shown in FIG. 20. The display 370 includes indicators 372, 374, 376, 378 and 380 which each indicate the MTF at a respective one of the selected locations within the transmitted beam. As discussed above, the modulation at a respective location within the transmitted beam is defined as follows: modulation = (maximum intensity - minimum intensity) ÷ (maximum intensity + minimum intensity) ; and the MTR at the respective location in the transmitted image is further defined as follows: MTR = modulation of image after transmission ÷ modulation of image before transmission. As discussed above, the sinusoidally-varying medium 48 causes the intensity of the transmitted beam to vary sinusoidally along a predetermined direction in the beam, and the video signals generated by the video system 22 correspondingly vary sinusoidally with respect to time and thus are indicative of the intensity pattern of the transmitted image. The maximum and minimum intensities used in calculating the modulation are each measured with respect to an intensity of the video signal corresponding to a "black" (dark or unilluminated) intensity. Those skilled in the art will note that the signal intensity corresponding to "black" is different from the "back porch" level of the video signal, which is typically lower. FIG. 21 depicts a graph 390 illustrating the definition of modulation at a location within a light beam. The graph 390 includes a curve 392 representing an intensity which varies sinusoidally along a predetermined direction. At a location defined by a range 394 along the predetermined direction, the intensity varies from a maximum intensity 396 at a distance 400 along the predetermined direction to a minimum intensity 398 at a distance 402 along the predetermined direction. Thus, the modulation at a location defined by the range 394 may be determined from the maximum intensity 396 and minimum intensity 398 in the manner defined above. In another embodiment, the maximum intensity used in the modulation determination is the average of the maximum intensities of two consecutive cycles, such as the intensities at distances 400 and 404. Using an average of two maximum intensities accounts for maximum intensities which vary significantly among consecutive cycles, such as is common at the periphery of the transmitted image where the intensity sharply declines. It is known in the art that the MTF value of a system is equal to the product of the MTF values of the components of the system. The above-described MTF values are generated in dependence on the signals generated by the frame grabber card, and represent the MTF value of the combination of the endoscope and the video system 22. However, since the video system is typically optically superior to the endoscope, a fixed correction factor can be calculated for the video system and used in determining the MTF of the endoscope alone. According to "Video Engineering" by Andrew Inglis, McGraw Hill, 1993, which is hereby expressly incorporated by reference as part of the present disclosure, a correction factor of approximately 0.96 is appropriate for video systems such as those used in the present invention. Furthermore, the precision micro- densitometer modulation calibration of the semi-transparent medium 48 also affects the MTF of the entire endoscope evaluation apparatus. The semi-transparent medium 48 provided by Sine Patterns, Inc. has a modulation calibration of 0.81366. Accordingly, the MTF value for the endoscope alone is determined by dividing the above-calculated MTF (which is equivalent to the MTR) by the following product: (0.96)*(0.81366) . Referring again to FIG. 20, each of the indicators 372, 374, 376, 378 and 380 further indicates whether an MTF value indicates either a "pass" or "fail" condition. In the preferred embodiment, each MTF value is compared to a predetermined MTF threshold. MTF values which are below the predetermined MTF threshold are considered "fail" values. If at least one of the plurality of MTF values is a fail value, the endoscope has failed the MTF test. Textual displays 382 (FIG. 20) and 366 (FIG. 19) indicate whether the endoscope has passed the MTF test. In the preferred embodiment, for 10 millimeter diameter endoscopes with 0 degree tip angles, the MTF threshold at the center of the transmitted beam is approximately 0.70, and at other locations in the transmitted beam is approximately 0.20. As is known in the art, a spatial frequency is defined by the number of cycles (transitions from a maximum intensity to a minimum intensity and back again) per unit of length. The semi-transparent medium 48 (FIG. 3a) is preferably implemented as the above-mentioned sinusoidally- varying medium having a spatial frequency of one cycle per millimeter. Thus, filtering a beam of light through this medium during the MTF test generates a beam having an intensity which varies approximately sinusoidally along a first direction in the generated beam at a spatial frequency of about one cycle per millimeter, and which is approximately constant along a second direction in the generated beam. The generated beam is transmitted through the endoscope and recorded by the video system 22 (FIG. 1) as set forth above. The video system 22 records the transmitted image in a conventional manner: the CCD camera sequentially scans in a horizontal scan direction from one end of the transmitted image to the other, defining a scan row, and the video system generates time-varying video signals indicative of a row of pixels for the scanned row. In other words, the video signals generated by the video system 22 correspondingly vary sinusoidally with respect to time and thus are indicative of the intensity pattern of the transmitted image along the scan row. After scanning a row, the CCD camera proceeds to scan the next row until all rows have been scanned and all pixels have been generated. With the sinusoidally-varying medium described above, each row across the transmitted beam has an approximately-sinusoidal intensity variation. The frequency of the transmitted beam, in units of cycles per degree of the apparent field of view of the endoscope, is defined not only by the spatial frequency of the medium but also by the distance between the medium and the endoscope tip. As is described below, this distance is selected so that the frequency of the transmitted beam is approximately six cycles per degree of apparent field of view. In accordance with a further aspect of the invention, it has been determined that MTF measurements at a single spatial frequency of approximately six cycles per degree of apparent field of view are an accurate indication of optical instrument performance. FIG. 22 is a schematic illustration provided for purposes of determining the frequency of the transmitted beam. The tip 418 of an exemplary endoscope 410 is spaced a predetermined distance "d" from a semi-transparent medium 416. The exemplary endoscope 410 has an actual field of view of seventy degrees, which is thirty five degrees to each side. The actual field of view is defined as the angular extent of an object visible through the endoscope subtended at the tip of the endoscope. Thus, the length "x" of the medium visible in each thirty five degree field of view is determined as follows: (1) x = (tan 35°) (d) = (0.7) (d) millimeters Accordingly, the length of the medium which lies in the entire seventy degree field of view is twice the length "x" as defined in equation (1) : (2) 2x = 2(d) (tan 35°) = (1.4) (d) millimeters In the preferred embodiment, since the medium 416 defines a spatial frequency of approximately one cycle per millimeter, the number of cycles across the medium in this direction is determined approximately as follows: (3) total cycles = (1 cycle/millimeter) (2x millimeters) = (1 cycle/millimeter) ((1.4)(d) millimeters) (1.4) (d) cycles in the apparent field of view As discussed above, in the preferred embodiment the desired frequency of the transmitted beam is six cycles per degree of apparent field of view. The exemplary endoscope 410 has an apparent field of view 412 of twelve degrees. The apparent field of view is the angle between the right and left sides of the image as subtended by the eye. The desired number of cycles across the medium in the apparent field of view is determined approximately as follows : (4) (6 cycles/degree) (12 degrees) = 72 cycles in the apparent field of view Accordingly, the value of "d" is determined from the equality of relationships (3) and (4) for the desired number of cycles in the field of view: (5) (1.4) (d) = 72 (6) d = 72 / 1.4 = 51.4 millimeters = 2.02 inches Thus, the tip 418 of the endoscope 410 is spaced approximately two inches from the medium 416. Since the distance d is known, the length of the medium which lies in the field of view is determined as follows: (7) 2x = (1.4) (d) = (1.4) (2.02 inches) = 2.83 inches Conventional video systems scan at a rate of approximately one frame every 1/30th of a second. Since each frame comprises a two-dimensional array which is 512 pixels x 512 pixels, the video system 22 scans 512 rows every 1/30th of a second. Thus, the video system scans one row every l/15360th of a second (one row every 65 microseconds) . Since, from relationship (4) above, there are seventy two cycles in the field of view, the video system 22 scans 72 cycles in 65 microseconds if the horizontal scan direction is substantially parallel to the direction along the medium which varies at one cycle per millimeter. The scan rate of 72 cycles in 65 microseconds defines a video frequency of the time-varying video signals which the video system generates : 72 cycles / 65 microseconds = 1.11 megahertz (MHz) Of course, the video frequency is easily determined for video systems which scan at a rate different than one frame every l/30th of a second, and for video systems which scan at a number of cycles in the apparent field of view different than 72 cycles. The time-varying video signals, like most signals, are at least partially corrupted by noise. In conventional video systems, the predominant form of noise is a color subcarrier signal having a frequency of approximately 3.57 MHz. The above-stated video frequency of 1.11 MHz is so close to the noise frequency of 3.57 MHz that a conventional low-pass filter, such as a Butterworth filter implemented in the frame grabber card, will not be able to substantially attenuate the noise signals without also attenuating the video signals. Thus, the filter will not be able to improve the signal-to-noise ratio. Two quantities which determine the video frequency, the spatial frequency of the sinusoidally-varying medium 48 and the scan time of the video system 22, cannot easily be adjusted. The spatial frequency of the sinusoidally-varying medium is selected for efficiently testing the endoscope, and the scan time of the video system cannot be changed without significant hardware redesign. Accordingly, the video frequency is preferably not adjusted by adjusting either of these two values. However, if the horizontal scan direction is transverse to the direction along the medium in which the intensity varies at one cycle per millimeter, then the video system scans less than 72 cycles in 65 microseconds. The number of cycles scanned in a row decreases as the scan direction becomes less parallel and more perpendicular to the direction of variance in the medium. As will be seen below, the frequency of the video signal will likewise decrease, further separating the video frequency from the noise frequency and thereby facilitating noise filtering. FIGS. 23a and 23b illustrate the manner in which the total number of cycles scanned depends on both the horizontal scan direction and the direction along the medium which varies at one cycle per millimeter. FIG. 23a shows in schematic form an exemplary medium 420 in which the transmittance varies sinusoidally along a direction 430. Maxima (or cycles) in the transmittance are indicated by reference numerals 421, 422, 424, 426, 428 and 429. Thus, the medium 420 illustrated in FIG. 23a includes six cycles along the direction 430. A horizontal scan direction 432 is substantially parallel to the direction 430 of the medium 420. Accordingly, a scan across the scan direction 432 crosses six cycles from one end of the medium 420 to the other across a distance 434. FIG. 23b shows in schematic form another exemplary semi-transparent medium 440 which is substantially identical to the medium 420 of FIG. 23a but rotated with respect to the horizontal scan direction. The medium 440 defines a transmittance which varies sinusoidally along a direction 450. Maxima (or minima) in the transmittance are indicated by reference numerals 441, 442, 444, 446, 448 and 449. Thus, the medium 440 includes six cycles along the direction 450. As shown, a horizontal scan direction 452 is transverse to the direction 450 of the medium 440. Accordingly, a scan across the scan direction 452 crosses less than six cycles from one end of the medium 440 to the other across a distance 454 equal to the distance 434 in FIG. 23a. Thus, decreasing the number of cycles scanned in a row by selecting a scan direction transverse to the direction of variance in the medium will likewise decrease the video frequency without changing the spatial frequency of the image. In fact, the angle between the scan direction and the direction of variance in the medium defines the decrease in the video frequency. The number of cycles scanned in a row is determined by the relationship: Cycles scanned = (Max Cycles) (cos θ) wherein: θ is the angle between the scan direction and the direction of variance in the medium; and Max Cycles is the number of cycles scanned when θ = 0. Similarly, the frequency of the video signal is determined by the relationship: Frequency = (Max Frequency) (cos θ) wherein: Max Frequency is the frequency when θ = 0. Thus, to divide the video frequency of 1.11 MHz by a factor of three, the angle θ is selected in accordance with the following relationship: Frequency = (Max Frequency) (cos θ) 1.11 / 3 = (1.11) (cos θ) 1/3 = cos θ θ = 71 degrees Thus, orienting the semi-transparent medium relative to the horizontal scan direction of the video system to form a 71 degree angle between the scan direction and the direction of variance in the medium reduces the video frequency approximately as follows: 1.11 MHz / 3 = 0.37 MHz. This reduced video frequency is more easily distinguished from the noise frequency of 3.57 MHz by a low pass filter. For example, a fourth-order Butterworth filter having a "cut-off" frequency of 0.66 MHz substantially attenuates the 3.57 MHz noise signal while attenuating the 0.37 MHz video signal by less than 0.1 dB. Of course, other values for the angle θ will reduce the video frequency by different amounts. For example, an angle of 40 degrees yields a decrease by a factor of 1.4, while an angle of 89 degrees yields a decrease by a factor of 57. Greater decrease factors may be produced by selecting angles which are even closer to 90 degrees, but selecting an angle of 90 degrees results in a frequency of zero. As is known in the art, the fourth-order Butterworth filter has overshoot and ringing characteristics for step input signals. However, according to the "Handbook of Filter Synthesis" by Anatol Zverev, John Wiley and Sons, Inc., 1967, which is hereby expressly incorporated by reference as part of the present disclosure, the overshoot and ringing is reduced to about 1% after a delay of 10 normalized periods of the filter cut-off frequency. This delay is, in this filter, only approximately 2.4 microseconds, which is less than 4.4% of the horizontal scan time and thus not a significant source of error. FIG. 24 depicts an exemplary graph 460 illustrating in simplified form the attenuation characteristics of a low- pass filter. The graph 460 defines a first set of frequencies 462 which are virtually unattenuated, and a second set of frequencies 464 which are substantially completely attenuated. A frequency 470 is the video frequency, such as 1.11 MHz, when the horizontal scan direction is parallel to the direction of variance in the medium. A frequency 466 is the video frequency, such as 0.37 MHz, after selecting a horizontal scan direction transverse to the direction of variance in the medium. A frequency 468 defines a threshold below which the filter does not substantially attenuate signals. Another threshold frequency 472 defines the frequencies above which the filter substantially completely attenuates signals. Finally, a frequency 474 is the noise frequency, such as 3.57 MHz. The filter substantially attenuates the noise frequency 474 since it is greater than the frequency 472. In addition, the filter passes substantially unattenuated the frequency 466 since it is less than the frequency 468. In response to a user command input through the GUI, the computer system 32 transmits any of the above- described displays to the printer 34. The printed display is useful in the analysis of test results, and thus in evaluating the performance characteristics of tested endoscopes, in that it may be transmitted (i.e., sent by mail, electronic mail or facsimile) to distant users unable to view, or otherwise access the monitor or computer system of FIG. 1. In the preferred embodiment, the computer system 32 (FIG. 1) further comprises a database for storing, for each endoscope tested, a unique identifier for the endoscope, the endoscope manufacturer, diameter, length and tip angle, any reported and observed problems with the endoscope, the time and date of testing, the reason for testing, the test results, and the evaluation of the results. Such a database allows the system of the present invention to evaluate changes in endoscope performance after repair operations and over the lifetime of the endoscope. The database can be implemented with a variety of commercial software products, such as Microsoft Access™ or Claris FileMaker Pro™. In FIGS. 25 through 26C the mounting arm and carrier of the test station 12 are illustrated in further detail. As best seen in FIG. 26A, the mounting arm 14 is pivotally coupled to the arm support 36 by an adjustable first hand-knob 544 for adjusting the angular position of the mounting arm relative to the carrier support 40. A first threaded shaft 546 is connected at one end to the first hand-knob 544, extends through an aperture 548 defined by the arm support 536, and in turn is threadedly received at its other end by the mounting arm 14. A second threaded shaft 547 is threadedly received at one end by the upper end of the mounting arm 14, and at its other end by a second hand-knob 549. The second threaded shaft 547 extends from the mounting arm 14 above an upper edge of the arm support 36. A pair of washers 550 are mounted on the second threaded shaft 547, one being interposed between the arm support 36 and the mounting arm 14, and the other between the second hand-knob 549 and a rear surface of the arm support. Once the mounting arm 14 is angularly adjusted to a selected position corresponding to the tip angle of the endoscope being tested, rotation of the first hand-knob 544 causes the knob to engage the arm support 542, and rotation of the second hand-knob 549 causes the pair of washers 550 to engage the arm support at its upper edge, thereby locking the mounting arm 14 in place. The mounting arm 14 is unlocked by rotating the first and second hand-knobs 544 and 549, respectively, in a direction opposite to that required to lock the arm in place. As shown in FIG. 2, to further aid in the proper positioning of the mounting arm 14, and of the endoscope being tested relative to the targets on the carrier 16, the arm support 36 preferably defines angular indicia incrementally spaced in an arcuate pattern adjacent to its upper edge. When an endoscope is tested, the mounting arm 14 is aligned with the angular indicia corresponding to the endoscope 's tip angle, thereby properly positioning the endoscope relative to the targets mounted on the carrier 16. While the mounting arm 14 of the present invention has been shown and described as being pivotally coupled to the arm support 36, the invention is not limited in this regard and other methods of coupling the mounting arm to the frame for movement relative to the carrier and its associated targets may be substituted for the one illustrated. For example, the mounting arm 14 could be coupled directly to the carrier support 40. As shown in FIGS. 2 and 25, the test station 12 also includes means for guiding the carrier 16 along the carrier support 40 relative to the mounting arm 14. Preferably, this means includes a groove defined by one of the carrier 16 and carrier support 40, and the other defines a guide received within the groove. As shown in FIG. 25, in the preferred embodiment, a first rail 554 is mounted on the carrier support 40 and is spaced in front of and extends approximately parallel to the arm support 36. A second rail 556 is also mounted on the carrier support 40 and is approximately parallel to, and spaced apart from the first rail 554, such that the first and second rails, 554 and 556 respectively, define a groove 558. As shown in FIG. 25, the carrier 16 includes a guide, preferably in the form of a depending foot 560 receivable within the groove 558, and as indicated by the arrows in FIG. 3, movable between an unlocked position where the foot 560 is spaced below a lip 562 of the second rail 556 for sliding the carrier along the groove, and a locked position with the foot 560 moved into engagement with the lip 562 for fixing the position of the carrier 16 along the groove. The mechanism by which the foot 560 is moved between the locked and unlocked positions includes a bushing 564 having a first cylindrical section 565 defining a knurled surface, and a second cylindrical section 566 having a reduced outer diameter in comparison to the first cylindrical section, the second cylindrical section being rotatably received within an aperture 567 extending through the carrier 16. A shaft 568 is connected on one end to the foot 560, is threadedly received through the bushing 564, and is connected on its other end to a knob 570. By rotating the knob 570 one quarter turn, the foot 560 is rotated until it abuts the rail 556, under the lip 562. Rotation of the knurled surface 565 of the bushing then causes the foot 560 to move between its locked and unlocked positions, as indicated by the arrows in FIG. 25. Referring to FIGS. 26B and 26C, the mounting arm 14 of the present invention includes a first support bracket 572 mounted on the upper end of the arm, and one of a plurality of different endoscope holders 574 slidably received and retained within the first support bracket. The endoscope holder 574 defines a first cylindrical body section 576, a second cylindrical body section 578 having a reduced outer diameter in comparison to the first body section, and a lip 580 between the two sections. The lip 80 functions as a stop, and is seated against the upper surface 582 of the first support bracket 572 when the endoscope holder 574 is received within the bracket. In order to retain the endoscope holder 574, the first support bracket 572 defines a split-collar forming an aperture 584 for receiving the second cylindrical body section 578 of the endoscope holder. A slot 586 is formed through the first support bracket 572, and a fastener 588 is threadedly engaged with the first support bracket through the slot to move the opposing sides of the bracket toward and away from each other with rotation of the fastener, and thereby engage and release the endoscope holder mounted within the bracket. A second support bracket 575 is spaced below the first support bracket and mounted to the base of the mounting arm 14, in order to engage and support the distal end of an endoscope at a predetermined distance from each target mounted on the carrier 16. As indicated above, in the preferred embodiment of the present invention, a plurality of endoscope holders 574 are provided, each for receiving a different size of endoscope. As best seen in FIG. 26B, the endoscope holder 574 defines a first aperture 590 extending through the first cylindrical body section 576 and having a first inner diameter Dl for receiving the eyepiece of an endoscope, and a second aperture 592 extending through the second cylindrical body section 578 and having a second inner diameter D2 for receiving the body portion of the endoscope. The first and second inner diameters, Dl and D2 respectively, vary for each of the respective endoscope holders depending on the configuration of the endoscope that the holder is designed to retain. In the preferred embodiment, the apparatus is adapted to accept endoscopes having bodies defining diameters within the range of approximately 1.9 through 10.0 millimeters, lengths within the range of approximately 4 inches through 13 inches, and tip angles within the range of approximately 0 degrees through 120 degrees. Still referring to FIG. 26B, the mounting arm 14 defines a slot 594 extending in its elongated or axial direction. As is best seen in FIG 26A, the first support bracket 572 includes a boss 596 extending therefrom and having a shape that is complimentary to the slot 594. The boss 596 is slidably received within the slot 594 for selectively positioning the first support bracket along the slot to accommodate endoscopes of differing lengths. The first support bracket 572 is locked into position along the slot by a fastener 598. Alternatively, and as shown in FIG. 26C, the mounting arm 14 may define a plurality of aperture pairs 500 spaced relative to each other at predetermined intervals for attaching the first support bracket to the mounting arm, and to thereby accommodate endoscopes of different lengths. Turning to FIG. 3A, the carrier 16 defines a mounting surface 102 for supporting the plurality of different targets, and four legs 504 for supporting the carrier on the carrier support 40. The carrier 16 also includes two pairs of adjustable abutment members 506 (only one pair shown in FIG. 3A) mounted on opposite sides of the carrier relative to each other, with each pair spaced apart from each other on the respective carrier side. As shown best in FIG. 25, each abutment member 506 includes a head 508 and a threaded shaft 510 connected at one end to the head and threadedly engaged at the other end with the respective side of the carrier. With the carrier 16 mounted on the carrier support 40, as shown in FIG. 2, the respective pairs of abutment members 506 are rotated into contact with the front face of the arm support 36 to thereby maintain the carrier in an aligned configuration relative to the mounting arm 14. Although the invention has been shown and described with respect to a preferred embodiment thereof, it would be understood by those skilled in the art that other various changes, omissions and additions thereto may be made without departing from the spirit and scope of the invention as defined in the appended claims. For example, there are other fiber-optic scopes, known as bore scopes, which are similar to endoscopes for use in medical applications, but have much larger length-to-diameter ratios. Bore scopes are used to examine the internal subassemblies in large engines, compressors and turbine machinery. Such bore scope may be tested and evaluated using the system of the present invention with minimal modification of the preferred embodiment presented herein. Accordingly, this detailed description of a preferred embodiment is to be taken in an illustrative, as opposed to a limiting sense.

Claims: What is claimed is; 1. A method for evaluating the performance of an endoscope, comprising: generating a beam of light defining a predetermined intensity pattern; transmitting the beam through the endoscope from a first end of the endoscope through a second end; generating signals indicative of the optical intensity of the beam after transmission through the second end of the endoscope at each of a plurality of predetermined locations within the beam. 2. The method of claim 1, wherein the step of generating the beam of light comprises: transmitting a beam of light in a direction from the second end through the first end, and in turn onto a reflective surface defining a substantially uniform reflectance. 3. The method of claim 2 , wherein the step of transmitting the beam of light onto a reflective surface comprises: transmitting a beam of light in a direction from the second end through the first end, and in turn onto a substantially nonspecular reflective surface defining an approximately uniform reflectance to thereby generate a nonspecular, reflected beam of approximately uniform intensity. 4. The method of claim 3, further comprising: selecting the intensity of the generated beam such that the endoscope attenuates the intensity at locations in a central region of the transmitted beam to an intensity above a first predetermined intensity, and attenuates the intensity at locations at the periphery of the transmitted beam to approximately zero. 5. The method of claim 3, further comprising selecting the intensity of the generated beam such that (i) the endoscope attenuates the intensity at locations in the central region of the transmitted beam to an intensity above a first predetermined intensity; (ii) the endoscope attenuates the intensity at locations between the center and the periphery of the transmitted beam to an intensity between the first predetermined intensity and a second predetermined intensity lower than the first predetermined intensity; and (iii) the endoscope attenuates the intensity at locations at the periphery of the transmitted beam to approximately zero . 6. The method of claim 3, further comprising: generating for each of a plurality of locations in the transmitted beam signals indicative of one of a plurality of intensity ranges including the intensity of the respective location. 7. The method of claim 2, wherein the step of transmitting the beam of light onto a reflective surface comprises : transmitting a beam of light in a direction from the second end through the first end, and in turn onto a mirror-like surface defining an approximately uniform reflectance to thereby generate a specular, reflected beam. 8. The method of claim 7, further comprising: selecting the intensity of the generated beam such that (i) the endoscope attenuates the intensity above a first predetermined intensity at locations in the transmitted beam corresponding to working fibers, and (ii) the endoscope attenuates the intensity to a second predetermined intensity less than the first predetermined intensity at locations in the transmitted beam corresponding to damaged fibers. 9. The method of claim 8 , wherein the generated beam is selected such that the endoscope attenuates the beam to approximately zero intensity at locations corresponding to damaged fibers. 10. The method of claim 1, wherein the step of generating the beam comprises : filtering a beam through a semi-transparent medium having a transmittance which varies periodically along at least one predetermined direction within the medium, thereby defining a generated beam having an intensity which varies periodically along the at least one predetermined direction; and further comprising the step of generating signals indicative of the modulation at a location in the beam transmitted through the second end in dependence on the signals indicative of intensities at predetermined locations. 11. The method of claim 10, wherein the step of filtering the beam comprises: filtering the beam through a semi-transparent medium having a transmittance which varies approximately sinusoidally along the medium in a first direction, and which is substantially constant along a second direction transverse to the first direction, thereby defining a generated beam having an intensity which varies approximately sinusoidally in the first direction. 12. The method of claim 10, further comprising: generating signals indicative of the intensity at a plurality of approximately collinear locations in the transmitted beam. 13. An apparatus for evaluating the performance of a endoscope, comprising: means for generating a beam of light defining a predetermined intensity pattern and for transmitting the beam through the endoscope from a first end through a second end; and means for generating signals indicative of the optical intensity of the beam after transmission through the second end of the endoscope at each of a plurality of predetermined locations within the beam. 14. The apparatus of claim 13 , wherein the means for generating the beam of light comprises a reflective surface defining a substantially uniform reflectance. 15. The apparatus of claim 13 , wherein the means for generating the beam of light comprises a nonspecular reflective surface. 16. The apparatus of claim 14, wherein the means for generating the beam of light comprises a mirror-like surface . 17. The apparatus of claim 13, wherein the means for generating the beam of light comprises a semi- transparent medium having a transmittance which varies periodically along the medium. 18. An apparatus for evaluating the performance of a endoscope, comprising: a nonspecular reflective surface; a mirror-like surface; a semi-transparent medium having a transmittance which varies periodically along the medium; a light source connectable between (i) a first position in which the light source transmits light through the endoscope from a second end through a first end of the endoscope and onto one of the nonspecular reflective surface and the mirror-like surface, and in turn back through the endoscope, and (ii) a second position in which the light source transmits light through the semi-transparent medium into the first end and through the second end of the endoscope; and means for generating a first set of signals indicative of the optical intensity of the beam after transmission through the second end of the endoscope at each of a plurality of predetermined locations within the beam. 19. The apparatus of claim 18, further comprising: means for generating a second set of signals responsive to the first set of signals which are indicative of the performance of the endoscope.

Inventors: ADAM JOSEPH, BEATRICE FINTON, ROSOW ERIC, YOUNGDAHL CURTIS, ADAM, JOSEPH, BEATRICE, FINTON, ROSOW, ERIC, YOUNGDAHL, CURTIS
Applicants: ADAM JOSEPH, BEATRICE FINTON, HARTFORD HOSPITAL, ROSOW ERIC, YOUNGDAHL CURTIS, ADAM, JOSEPH, BEATRICE, FINTON, ROSOW, ERIC, YOUNGDAHL, CURTIS
Application year: 1998
Main classification: G01N21
IPC codes: A61B1, G01M11