the following detailed description describes a number of preferred embodiments of various aspects of the invention . these embodiments are examples only of the full scope of what is enabled by this disclosure , and are not intended to limit the scope of the claims . the present invention uses multispectral imaging , in which a plurality of light wavelengths are concurrently measured to obtain information about a target . in one embodiment , a reflectance method is used , in which multiband filters are used to simultaneously record specific wavelengths . multispectral imaging is commonly used in satellite imaging , but has not been widely applied to the eye . often , multispectral imaging is accomplished by the use of multiple bandpass filters , with each selected bandwidth being imaged concurrently by different detectors . the use of multiple detectors would be difficult and expensive in clinical imaging of patients &# 39 ; eyes . fundus cameras at one time used film for photographic documentation . with development of improved high resolution monochromatic charged coupled devices ( ccds ), monochromatic film use was replaced with monochromatic digital imaging . it was common to use color slide film to record color images . later development of sensitive , high - speed color digital cameras has led to the replacement of color film with electronic detectors in imaging the fundus . digital color cameras use monochromatic ccds with a varying pattern of color filters in front of the individual elements of the ccd , so as to provide a color separation for the various monochromatic detectors . in this way , a plurality of grayscale channels can be output , each corresponding to one of the separated colors . the most common method for using monochromatic ccds in digital color cameras is to use a filter having a “ bayer ” pattern ( known as a “ bayer filter ”). a schematic representation of a ccd with a bayer filter is shown in fig1 . as shown in fig1 , the bayer filter 104 is overlaid on ccd array 102 comprising individual monochromatic ccd elements 103 etc . the bayer filter 104 has a checkerboard pattern of red , green , and blue filters , each positioned in front of a ccd element . the red , green and blue components , respectively , of incoming light 106 are passed by the respective red , green and blue filter elements 107 , 108 and 109 , to illuminate the respective underlying sets 110 , 111 and 112 of ccd elements . thus , the spectral sensitivity of each monochromatic ccd elements is modified by the filter element overlaying it . the three sets of ccd elements , 110 , 111 and 112 produce three color - separated grayscale channels , 1 a , 1 b and 1 c . by maintaining a representation of the coordinates of each ccd element in the outgoing signal , topographic , color - separated grayscale signals may be obtained in raster or other suitable form . one problem , however , is that the color separation provided by the above - described arrangement is not very sharply defined . since the design goal of a digital color camera is to produce accurate and pleasing color images , the red , green , and blue filters are not particularly specific and show significant overlap . thus , the grayscale data obtained from a typical digital color camera is not sharply defined in the red , green and blue color ranges . the spectral characteristics of a typical digital color camera employing a ccd array with a bayer filter is shown in curves 202 , 204 and 206 of fig2 . it can be seen that there are significant spectral overlap regions between the bayer filter elements , at 208 and 210 . the absorption curve 214 for macular pigment is superimposed for comparison . as can be observed , while centered in the blue region 206 , significant portions of this absorption curve also lies in the passband 204 of the green bayer filter . this overlap would reduce the accuracy of any measurement of pigment by comparing grayscale images obtained from prior art instrumentation . the present invention , in one embodiment , uses a multiband filter to sharpen the color resolution of a digital color fundus camera . using such a filter , it is possible to select red , green , or blue wavelengths and have the corresponding wavelengths imaged in the corresponding red , green , and blue channels of the color ccd . such a method is particularly effective if the bandpass regions are selected so as to lie between and thereby avoid all or a substantial portion of the above - described spectral overlap areas between the filter responses of the bayer filter within the camera &# 39 ; s ccd . the result in such a case is to effectively sharpen the spectral response of the apparatus so that accurate measurements can be made . one embodiment of a fundus camera - based system for practicing the methods of the present invention is shown in fig3 . fig3 is a simplified schematic diagram showing a fundus camera - based system for practicing the present invention , and an exemplary placement of the filters used for macular pigment imaging . in fig3 , 301 is the light source , which is generally a halogen light for viewing and a xenon flash lamp for photography . light produced travels through condenser 302 and relay 303 lenses to reach the multiband passband filter at 304 . this filter can be shifted into the optical path as need for macular pigment photography . the light is reflected by mirror 305 through relay lens 306 to the holed or fenestrated mirror 307 . this directs light toward the eye through objective lens 308 into the eye 309 . light returning from the eye is focused by the objective lens through the hole in mirror 307 . the barrier filter 310 is placed such that it can be brought into position to block unwanted wavelengths of returning light if needed . the light passes through focusing 311 and imaging lenses 312 and passes through the area occupied by a switching mirror 313 . when the operator is viewing the fundus , light is directed to mirrors 314 and 315 through the eyepiece 16 to the operator &# 39 ; s eye 317 . when a photograph is taken the switching mirror position drops down and light is reflected to mirror 318 through relay lens 319 to the image - recording device 320 . while this conceivably could be a film camera , in practical use it is a ccd camera connected electronically 321 to a computer and display 322 . images can be recorded digitally by frame capture . preferably , multiband filter 304 is a single filter having multiple optical bandpass regious . such multiband bandpass filters are manufactured using ion beam sputtering and can obtain increased brightness and very accurate selection of bandpass wavelengths . these filters are commonly used for fluorescence microscopy . they are occasionally used for color photography . these filters can be designed to allow multiple bands of selected wavelengths to pass with blocking of unwanted wavelengths to equal or exceed 5 od . in the reflectance method used in one embodiment of the invention , multiband filters are used to record specific wavelengths simultaneously . the filter used for macular pigment imaging preferably has narrow bandpass regions near 465 nm , 535 nm , and 630 nm . these correspond to blue , green , and red visible wavelengths , and are represented in the blue , green , and red channels of the fundus camera , respectively . this allows simultaneous recording of three bands of information at no increase in cost for detectors . when combined , the resultant image is a full color image that looks remarkably like a regular color picture . the color information can be easily deconstructed into component channels . since each of the separate channels was taken at the same time with the same camera and detector they have the same field of view , magnification , and lighting . this permits ratiometric evaluation without the need for any preliminary image registration steps . fig4 shows the idealized wavelength selection of the preferred embodiment multiband filter described above , with red green and blue bandpass regions 402 , 404 and 406 respectively . fig5 shows the filter bandpass regions of fig4 overlayed on the spectral diagram of fig2 . it can be seen that in this representation , bandpass region 406 captures the ( blue ) peak of the macular pigment absorption curve 214 , whereas bandpass region 404 captures a green signal including very little or none of the spectral region of macular pigment absorption . to calculate the amount of macular pigment it is customary to calculate a ratio of the reflectance of the two wavelengths at two locations in the fundus , one within the region of the macula and the other in the periphery area outside of the region where there is deposition of the macular pigment . the optical density of the macular pigment is calculated as the log ( macula reflλ 1 / macula reflλ 2 )− log ( periphery reflλ 1 / periphery reflλ 2 ), where refl is the reflectance at either the long wavelength ( λ 1 ) or the short wavelength ( λ 2 ). the invention also concerns methods to display the spectral information . the typical fundus camera acquires a high resolution photograph of the eye that encompasses an angular measurement of approximately 50 degrees . the image may be acquired by a computer and processed digitally . only the central portion of this is needed , and a rectangular area is selected . in one embodiment of the present system , as shown in fig6 , a rectangle 601 measuring 1640 × 1435 pixels per side is used which represents an area of approximately 8 × 7 mm . a circular region 602 in the central 1230 pixels is used to calculate the ratio macula reflλ 1 / macula reflλ 2 and the remaining portion 603 of the rectangle is used to calculate periphery reflλ 1 / periphery reflλ 2 . the green channel information is divided by the blue channel . this produces a grayscale image where the macular pigment appears bright . however there may be a general level of gray visible outside of the region of interest caused by scatter , etc . the circular area 602 , which corresponds to a 6 mm diameter circle centered on the posterior pole of the eye is measured within this square . the portion of the rectangle 603 not included in the central 6 mm circle is assumed to have negligible amounts of macular pigment . the mean grayscale level of this region is measured . this grayscale level is subtracted from the individual values of the pixels in the entire square . the resultant image has black regions where there is no macular pigment and varying levels of gray where there is pigment . the human eye is not good at differentiating small changes in grayscale so , preferably , the images are given a pseudocolor . this helps differentiate small differences in the grayscale upon visual inspection . in one embodiment , as illustrated in fig7 , the pseudocolor is mapped to the grayscale by a method wherein the color assigned varies according to the underlying grayscale value , which in turn varies with the amount of macular pigment . the colors may be arranged in a gradient . in one embodiment , this gradient generally follows the order of the spectrum from red to violet , except that , because it is difficult to see the difference between blue , indigo and violet , the gradient was created such that the colors vary from black to blue for absent or nearly absent levels of pigment . thus , the gradient map colors in that embodiment start at black and then range the colors of the rainbow from blue to green , yellow , orange and red , with white added to represent the greatest value , for increasing amounts of the underlying grayscale value . the mean value of the central 500 microns of the macula ( 604 in fig6 ) is measured . this grayscale value is compared with a nomogram of values . the grayscale value of the person being tested is put into one of five groups based on the quintiles of normal distribution of the amounts of macular pigment in the general population . white is assigned to those in the highest quintile , red the second quintile , orange the middle quintile , yellow next , and green the lowest quintile . the rest of the pseudocolor map follows from the highest color down . this allows the examiner to rapidly estimate the amount of macular pigment present as compared with normative data . in addition , each channel of output from the camera can be viewed in isolation to gain additional information about the ocular fundus . alterations in the nerve fiber layer of the eye can often be best visualized by using short wavelengths of light as obtained with the blue portion of the filter . the green channel generally supplies the highest spatial resolution because there are more green sensitive elements in the color ccd . the red channel affords better visualization of deeper structures within the retina . ratiometric comparisons between various channels , or composites of more than one channel can improve visualization as required . for example , an average of the red and green channels may be performed , and the average used to normalize the blue channel by dividing the blue channel with the red / green information , thereby improving contrast . accordingly , the present invention provides a multiwavelength , topographic analysis of macular pigment , acquired with a single photograph , using commonly available equipment and commercially obtainable filters , produces highly useful and accurate data regarding macular pigment , and provides representations of the data in forms most advantageous for visual inspection by the opthalmologic practitioner . it should be apparent from the foregoing , therefore , that the present invention achieves its objects and overcomes many of the shortcomings of the prior art . although the present invention has been described with specific embodiments , a variety of changes , substitutions , variations , alterations , and modifications in accordance with the principles and apparatus described herein may be readily suggested by this disclosure to one skilled in the art . it is intended that the invention encompass all such changes , substitutions , variations , alterations , and modifications as fall within the scope and spirit of the following claims .