referring now to fig1 , an imaging spectrometer 10 of the present invention may provide for a housing 12 that may be manipulated by hand to view an object area 24 of the skin of a patient 14 . a tubular focus guide 16 may extend from the bottom of the housing 12 so that an optical assembly 18 within the housing may be precisely located with respect to the object area 24 at a desired focal distance . referring also to fig2 , the tubular focus guide 16 may surround an objective lens 20 of the optical assembly 18 , which is preferably a fixed focus lens , whose imaging characteristics match the length of the tubular focus guide 16 . a series of different fixed focal length lenses or a variable focus lens and auto focusing mechanism may also be used in an alternative embodiment . a set of light emitting diodes 22 may be arranged in a ring about the objective lens 20 inside the tubular focus guide 16 to provide even illumination of the object area 24 on skin of the patient within the tubular focus guide 16 . alternatively standard incandescent type or fluorescent bulbs may be used . the focus guide 16 may be transparent for ease of positioning on the imaging spectrometer 10 over a desired object area 24 or may be opaque to block interference from external illumination sources with location of the focus guide over the desired object area 24 being done by viewing of an electronic image to be described . the imaging spectrometer 10 may be wholly contained within the housing 12 or may transmit image data via a cord 41 or a wireless transmitter ( not shown ) to remote image processing circuitry 43 , as will be described . all or part of the analysis to be described may be done remotely , for example , by transmitting data directly to the physician &# 39 ; s office for processing or review . referring now to fig3 , the light emitting diodes 22 or other illumination source may produce light having a non - uniform spectrum 25 being a function of the construction of white light emitting diodes ( made up of three colored light emitting diodes ) as well as variations in the manufacturing process . this spectrum 25 may be measured and used for a normalization as will be described below . referring now to fig4 and 5 , the objective lens 20 may be aligned and focused on the object area 24 of the skin in the area of a suspicious feature 26 . the object area 24 is then illuminated by the light emitting diodes 22 and the reflected light is collected by the objective lens 20 and passed to a micro - lens array 27 . the micro - lens array is a set of lenses , either standard or anamorphic lenses , arranged contiguously over an area to capture substantially all the light passing through the area and provide multiple focal points , one focal point associated with each lens . the micro - lens array 27 thereby effectively divides the object area 24 formed of contiguous object elements 28 and remaps the light from the continuous object elements 28 to corresponding light points 30 in a pupil plane 32 . each light point 30 generally has a smaller spatial extent than the object elements 28 provided the object elements 28 are sufficiently small to present an essentially constant field with no or little spatial variation . this constant field of each object element 28 is transformed by each lens of the micro - lens array 27 to a single , intensity value at the light point 30 . thus , light points 30 provide spatially compressed versions of object elements 28 retaining the same spectral content and total energy of the object elements 28 . in this embodiment , substantially all of the light from the object area 24 is captured and remapped to the pupil plane 32 . the pupil plane 32 is aligned with a first object plane of a spectrometer 34 which receives the light points 30 and disperses them according to frequency onto an image ( spectrum ) plane 36 aligned with the face of an image detector 38 , for example , a charge coupled device ( ccd ) detector , which maybe a broadband monochromatic sensor . the dispersion in this case may be done by means of a prism 40 eliminating the multiple orders of spectrum produced by a grating ; however , the invention contemplates that a grating may also be used by proper design of the spectrometer 34 . the dispersion axis of the prism 40 is oriented at an angle with respect to rows and columns of lenses of the micro - lens array 27 so that the light from each of the light points 30 in the pupil plane 32 are spread into a separate spectra 42 extending in interleaved fashion without interference with each other on the surface of the image detector 38 . spectral data 45 , representing intensity values acquired from the image detector 38 at defined locations corresponding to particular frequencies of light in the spectra 42 , are received by image processing circuitry 43 . the pixel size of the image detector 38 is sufficiently small to allow multipoint measurements ( e . g ., 16 - 100 measurements ) of each spectrum 42 permitting multiple different frequency bands for each object element 28 of the object area 24 to be resolved and detected . this spectral data 45 provides intensity and location information that may be used to fully characterize the spectra 42 . the spectra 42 each provide one row of a data cube 47 where position along the row provides intensity values as a function of wavelength or frequency . the location of the row in the data cube 47 , in perpendicular coordinates x and y , correspond to the x and y location of the object elements 28 in the object area 24 forming the light points 30 . thus , one data acquisition may produce a data cube 47 of spectral and spatial data . additional discussion of the operation of a spectrometer suitable for use in the present invention for spectrometer 34 , is described in detail in u . s . patent application 2006 / 0072109 , naming the inventor of this application , filed apr . 6 , 2006 and hereby incorporated by reference . referring still to fig4 and 5 , spectral data 45 of the spectrum plane 36 is provided to image processing circuitry 43 , as will be described in additional detail below . the image processing circuitry 43 may be incorporated into the housing 12 of the imaging spectrometer 10 or in a remote computer connected to the imaging spectrometer 10 by means of a cable 47 or wireless systems such as bluetooth transmitters and the like . referring to fig4 and 6 , the imaging spectrometer 10 processes the spectral data 45 to generate an electronic image 44 by integrating the energy in each spectra 42 over frequency and mapping that total energy , according to the known geometry of the optical assembly 18 , back to corresponding image elements 46 having the same geometrical relationship as the object element 28 . no image data is lost in this process ( in terms of feature resolution ) provided that the object elements 28 are less than half the size of any feature desired to be resolved . appropriate selection of the micro - lens array 27 may ensure this condition . the electronic image 44 generated by the image processing circuitry 43 may be a monochromatic image or may be a color image , the later generated by partitioning each spectrum 42 into bands approximating the three primary additive colors . alternatively , the electronic image may be constructed from other portions of the spectra 42 to create false color images or band limited images . similarly , weighting may be applied to the colors of the spectra to provide color - weighted images . it will be understood from the above description that the imaging spectrometer 10 may thus receive light in each frame of data , from the entire object area 24 to produce at once both spectral data 45 and an electronic image 44 for all the contiguous object elements 28 in the object area 24 ensuring accurate registration between the electronic image 44 and the spectral data 45 with reduced distortion caused by motion of the imaging spectrometer 10 . referring now to fig6 , the image processing circuitry 43 may further process the collected multipoint spectral data 45 , as indicated by process block 50 , and multipoint electronic image 44 , as indicated by process block 52 . this processing may be by means of an electronic computer ( not shown ) executing a stored program to process digital values representing the spectral data 45 and the electronic image 44 . first , as indicated by process block 54 , and referring again to fig3 , each spectrum 42 of the spectral data 45 ( shown in fig4 ) may be normalized to the spectrum 25 of the known incident light of the light emitting diodes 22 or other light source . this normalization may simply divide each point of the spectral data 45 for each spectrum 42 by the corresponding point of the spectrum 25 to compensate for changes in intensity of the illumination at different frequencies . at process block 56 , the corrected spectral data 45 may be analyzed to extract spectral features . in the simplest case , predefined and stored reference spectrum frequency bands and normalized intensities for those bands , for known healthy and cancerous tissues , may be compared to corresponding bands and intensities of the tissue imaged by the present invention . both the reference and actually measured spectral values may be normalized to have comparable total light energy , the total light energy being the integral of the spectra between two predetermined frequencies . this approach allows different spectral bands to be isolated or given greater weight in the analysis process . alternatively , a library of normalized reference spectra for known healthy and cancerous tissues may be correlated with the measured spectra to identify a closest match . the spectral feature extraction process may be augmented by the step of taking an initial scan of the patient &# 39 ; s skin near the region of the suspicious feature 26 but believed to be cancer free , or using regions in the data image away from the suspicious feature that are believed to be cancer free to provide a patient reference spectrum that may be used to compensate ( for example , by looking at only spectral differences between these two spectra ) for variations in underlying tissue pigmentation among individuals and lighting differences between frames . in this latter case , the reference spectral values may also be difference values . as an alternative to identifying separate cancer free areas , the image processor 43 may normalize all spectra to an average of an entire frame , and in this way correct for variations due to illumination and skin color , discolorations in the skin and externally scattered light under the assumption that the image area is large enough to contain a healthy skin sample . the present invention contemplates that the spectral feature extraction may be informed by the electronic image 44 and , in particular , by an image feature extraction performed at process block 58 in which the area of the suspicious feature 26 is demarcated using standard image processing techniques such as morphological analysis . in this case , the electronic image 44 may be used to identify regions of likely healthy tissue and regions of suspicious tissue so that the spectral features of these two regions may be compared as described above automatically , or with operator oversight . in this case , the image guides the spectral analysis . the image may also be used to provide areas over which the spectra will be averaged to increase statistical reliability or to provide weighting of the significance of spectral data 45 from different regions . alternatively , the image feature extraction of process block 52 may be used independently to assess a demarcated area of the skin for cancer using the image based tests of asymmetry , irregular border , color and diameter ( the abc &# 39 ; s of skin cancer detection ). this demarcation process , in turn , may be informed by the spectral analysis of process block 56 , for example , by defining the boundary of the suspicious feature 26 by spectral features that may not be readily apparent to the human eye . information from the image feature extractor of process block 58 and the spectral feature extraction of process block 56 may be weighted and combined by a rules engine 60 operating using a set of expert rules , templates or statistically derived algorithms to identify whether cancer is likely based on both spectral and image measurements . in addition , the information from the spectral feature extraction of process block 56 and the image feature extractor of process block 58 may be provided to an image generator 62 which may display on a display 64 an image 66 showing a conventional image of the object area 24 as would be visible to a human observer , and a false color image 68 superimposed on that image either identifying particular spectral features or identifying regions , per the rules engine 60 , where cancerous tissue may be likely . one or more quantitative values 74 may also be displayed indicating for example skin area , confidence values and the like . referring now to fig7 , in an alternative embodiment of the present invention , the objective lens 20 may be followed by a fiber optic remapper 71 . the fiber optic remapper 71 may have a front face 70 consisting of the bundled ends of optical fibers arranged over a rectangular area at the image plane of the objective lens 20 to receive light from the objective lens for predetermined object elements 28 . the optical fibers are then routed separately to a rear face 72 where the ends of the fibers have been rearranged into a single continuous line . the rear face 72 of the fiber optic remapper 71 sits at the image plane of the spectrometer 34 such as that described above . in this case , and referring fig8 , the spectra 42 may extend an arbitrary distance , providing potentially greater spectral resolution . other methods of “ slicing ” the image , including the use of mirror arrays and the like , are also envisioned . in yet a further embodiment , ( not shown ) the remapping may simply sample small areas of the object plane by blocking other areas . this is not a preferred embodiment , but can provide many of other benefits of the invention . while the preferred embodiment reconstructs image data from the spectral data , the invention also contemplates that the image could be generated using a beam splitter and second image detector 38 . it is specifically intended that the present invention not be limited to the embodiments and illustrations contained herein , but include modified forms of those embodiments including portions of the embodiments and combinations of elements of different embodiments as come within the scope of the following claims .