fig1 ( a ) depicts an exemplary embodiment of a laser source system ( e . g ., which can include a 1050 nm swept laser source ) provided in a linear cavity configuration according to the present invention . as shown in this figure , a gain medium 10 can be provided , such as a bi - directional semiconductor optical amplifier ( qphotonics , inc ., qsoa - 1050 ) which may be driven at an injection current level of 400 ma . one port of the amplifier can be coupled to a wavelength - scanning filter 20 that may comprise a diffraction grating 30 ( 1200 lines / mm ), a telescope consisting of two lenses 40 , 42 with respective focal lengths of 100 and 50 mm , and a polygon mirror scanner 50 ( e . g ., lincoln lasers , inc ., 40 facets ). the design bandwidth and free spectral range of the filter can be approximately 0 . 1 nm and 61 nm , respectively . the amplifier &# 39 ; s other port can be spliced to connect to a loop mirror which may include a 50 / 50 coupler 60 . a sagnac loop 70 can also act as an output coupler . the reflectivity and output coupling ratio can be complementary , and may be optimized by adjusting a polarization controller 80 to tune the amount of the birefringence - induced non - reciprocity in the loop . the linear - cavity configuration can also be used instead of or together with conventional ring cavity designs , since low - loss low - cost circulators and isolators may not be readily available at 1050 nm . sweep repetition rates of up to 36 khz may be achieved with 100 % duty cycle , which may represent a significant improvement over previously demonstrated swept lasers in the 1050 nm region that offered tuning rates of & lt ; 1 khz . in an ofdi system according to one exemplary embodiment of the present invention , the laser can be operated at a wavelength sweep rate of about 18 . 8 khz , thus producing a polarized output with an average output power of 2 . 7 mw . fig1 ( b ) depicts an exemplary embodiment of an optical frequency domain imaging ( ofdi ) system according to the present invention . for example , it is possible to use a swept laser can be used as a light source 100 . this exemplary system further comprises a fiber - optic interferometer 110 , a beam scanner 120 , a detector 130 and a computer 140 . a sample arm 150 ( e . g ., 30 % port ) can be connected to a two - axis galvanometer scanner apparatus 120 which may be designed for a retinal imaging . a focal beam size can be approximately 10 μm in tissue ( e . g ., index = 1 . 38 ). the optical power level at an entrance pupil of an eye 160 can be measured to be about 550 μw , which is well below the 1 . 9 - mw maximum exposure level at λ = 1050 nm according to the ansi laser safety standards . a reference arm 170 ( e . g ., 70 % port ) can utilize a transmission - type variable delay line 180 and a 10 % tap coupler 182 to generate sampling trigger signals for acquiring data . as shown in fig1 ( b ), a neutral density ( nd ) attenuator 184 may be used to obtain an optimal reference - arm power . light returning from the sample can be combined with the reference light at a 50 / 50 coupler 190 . resulting interference signals can be measured using an ingaas dual - balanced detector 140 ( e . g ., new focus , inc ., 1811 ). a signal provided by the balanced detector 140 can be further amplified ( e . g ., by 10 db ), low - pass filtered , and digitized at 10 ms / s using , e . g ., a 12 - bit data acquisition board ( national instruments , inc ., pci - 6115 ). for example , when sampling a 512 samples during each a - line scan , the imaging depth range determined by the spectral sampling interval can be about 2 . 44 mm in air . fig2 ( a ) depicts an exemplary output spectrum measured using an optical spectrum analyzer in peak - hold mode ( with resolution = 0 . 1 nm ). the exemplary output spectrum spanned from 1019 to 1081 nm over a range of 62 nm determined by the free spectral range of the filter . the spectral range coincided with a local transparent window of the eye . the roundtrip optical absorption in human vitreous and aqueous humors can be estimated to be between about 2db and 5 db based on known absorption characteristics of water ( as shown in fig2 ( a )). using a variable - delay michelson interferometer , it is possible to measure the coherence length of the laser output , defined as the roundtrip delay resulting in 50 % visibility , to be approximately 4 . 4 mm in air . from this value , it is possible to determine an instantaneous line width of laser output to be 0 . 11 nm . in fig2 ( a ), a peak - hold output spectrum 200 and an optical absorption curve 205 are provided in water for a 42 - mm propagation distance corresponding to a roundtrip in a typical human vitreous . fig2 ( b ) shows a graph of a time domain exemplary oscilloscope output trace 210 of a laser output indicating 100 % tuning duty cycle at 18 . 8 khz ( single shot , 5 - mhz detection bandwidth ). the y - axis of the trace graph of fig2 ( b ) represents an instantaneous optical power . the total power of amplified spontaneous emission ( ase ) in the output , measured by blocking the intracavity beam in the polygon filter , is shown as about 1 . 1 mw . since ase is significantly suppressed during lasing , it is expected that the ase level in the laser output may be negligible . the laser output exhibited significant intensity fluctuations (˜ 10 % pp ) due to an etalon effect originating from relatively large facet reflections at the soa chip with a thickness equivalent to 2 . 5 mm in air . in the exemplary embodiment of the imaging system , the etalon effect can cause ghost images (− 30 db ) by optical aliasing . an exemplary embodiment of the ofdi system and exemplary optimized operating parameters can be provided to maximize the snr using a partial reflector ( neutral density filter and metal mirror ) as a sample . an exemplary preferable reference arm power for maximal snr may be 2 . 6 μw at each detection port . this relatively low value can be attributed to the relatively large intensity noise of the laser that may not be completely suppressed in the dual balanced detection . exemplary data processing according to an exemplary embodiment of the present invention can include reference subtraction , envelope apodization or windowing , interpolation to correct for nonlinear k - space tuning , and dispersion correction . for example , subtracting the reference from the interference signals can eliminate image artifacts due to a non - uniform spectral envelope of the laser source . apodizing the interference fringes by imposing a appropriate windowing technique can decrease the sidebands of point spread functions and improve image contrast . this exemplary embodiment of the process according to the present invention may come at a resolution loss and snr ( due to a reduced integration time ). it is possible to use a gaussian window to yield a desirable compromise in contrast and resolution ( e . g ., at 1050 - nm ). since the detector signal may not be sampled in constant time intervals , whereas the tuning curve of our laser was not linear in k - space , interpolating the interference signal may be preferable to reduce or avoid image blurring . upon completing the exemplary interpolation , the signal may be further corrected for the chromatic dispersion in the interferometer as well as in the sample , e . g ., by multiplying a predetermined phase function . fig3 shows exemplary a - line profiles and / or point spread functions 220 measured at various path length differences of the interferometer . for this measurement , we used a neutral density attenuator ( 73 db ) and gold - coated mirror in the sample arm , and the path length was varied by moving the reference mirror . the maximum snr is 25 d . that corresponds to a maximum sensitivity of 98 db . the theoretical shot - noise limit of sensitivity is calculated to be 109 db ; the 11 - db deficiency in sensitivity of our system seems reasonable , considering that the residual laser intensity noise , imperfect polarization alignment between the sample and reference light , and gaussian windowing , among many other practical details , contributed to snr loss . for example , to facilitate the exemplary snr analysis , each exemplary curve plotted was obtained by an average over 500 consecutive scans at a constant depth , and a simple numerical subtraction was performed to make the noise floor flat . ghost artifacts marked as asterisks 230 were caused by the etalon effect in the laser source are shown in this figure . as indicated in fig3 , the sensitivity was decreased to 92 db as the path length increased to a depth of 2 . 4 mm , due to the finite coherence length of the laser output . as compared to the conventional time - domain systems that use a broadband source at 1040 nm , the exemplary embodiment of the system according to the present invention provides a higher sensitivity , e . g ., at a 100 - fold faster image acquisition speed and one sixth of sample arm power . the high sensitivity and depth range of the exemplary embodiment of the system according to the present invention compare favorably with exemplary sd - oct systems that use broadband sources in the 800 - 900 nm spectral range . due to the absorption by water in the eye , the actual snr for the human retina is likely 3 - 4 db lower than the values measured with the mirror sample . based on the source spectrum ( as shown in fig2 ( a )) and the gaussian window function used , the theoretical axial resolution can be determined to be about 13 μm in air ; the measured values may be 14 - 16 μm , increasing with the depth . errors in interpolation and dispersion compensation due to higher order terms may account for the discrepancy . exemplary video - rate imaging of retina , optic disk , and choroid in vivo exemplary ofdi imaging was conducted on two healthy volunteers ( a : 36 - year - old asian male , b : 41 - year - old caucasian male ) using the exemplary embodiments of the system , process and arrangement according to the present invention . the exemplary ofdi system acquired 18 , 800 a - lines continuously over 10 - 20 seconds as the focused sample beam was scanned over an area of 6 mm ( horizontal ) by 5 . 2 mm ( vertical ) across the macular region in the retina . fig4 shows a sequence 250 of images of the fovea and optic disk of the sample recorded from volunteer a at a frame rate of 18 . 8 hz in 10 . 6 seconds . each image frame was constructed from 1 , 000 a - line scans with an inverse grayscale table mapping to the reflectivity range over 47 db , with each frame spanning over 6 . 0 mm ( horizontal ) and 1 . 8 mm ( depth ) in tissue . for example , 200 frames were acquired in 10 . 6 seconds to screen a tissue area with a vertical span of 5 . 2 mm . the anatomical layers in the retina are visualized and correlate well with previously published oct images and histological findings . fig5 a depicts an expanded exemplary image of fovea extracted from the three - dimensional data set using the exemplary embodiments of the system , process and arrangement according to the present invention . the exemplary ofdi image of fig5 a indicates a deep penetration into the choroid nearly up to the interface with the sclera , visualizing densely - packed choroidal capillaries and vessels . to assess the penetration of the exemplary embodiments of the system , process and arrangement according to the present invention , the two volunteers a and b can be three - dimensionally imaged using both the ofdi system and the sd - oct system previously developed for video - rate retinal imaging . the sd - oct system employed a super luminescent diode with a center wavelength of 840 nm and a 3 - db spectral bandwidth of 50 nm , offering an axial resolution of 8 - 9 nm in air . at an a - line rate of 29 khz and a sample arm power level of 600 μw , the sd - oct system offered a peak sensitivity of 98 db at zero delay that decreased to 82 db at the maximum ranging depth of 2 . 2 mm in air . fig5 a - 5f illustrate side - by - side comparisons of the ofdi and sd - oct images near the foveae and optic disks of the two volunteers a and b . for example , fig5 a and 5c shows ofdi images at fovea and optic nerve head from the volunteer a . fig5 b and 5d illustrate sd - oct images from the same person at similar tissue locations . fig5 e and 5f provide the ofdi and sd - oct images , respectively , obtained from volunteer b . for example , as shown , the ofdi images exhibit considerably deeper penetration in tissue than the sd - oct images in most if not in all data sets . such large penetration depth may stem from both the high system sensitivity and long source wavelength . despite the relatively large axial resolution of ˜ 11 μm in tissue , the ofdi system can visualize the anatomical layered structure in the retina ( as shown in fig5 a ), rnfl , retinal nerve fiber layer , ipl , inner plexiform layer , inl ; inner nuclear layer , opl ; outer plexiform layer , onl ; outer nuclear layer , iprl ; interface between the inner and outer segments of the photoreceptor layer , rpe ; retinal pigmented epithelium , and c ; choriocapillaris and choroid . as shown in these figures , the ofdi images exhibit considerably deeper penetration into the choroid compared to the sd - oct images , whereas the higher axial resolution in the sd - oct images provide better contrast between retinal layers . the lower absorption and scattering in rpe at 1050 nm than 840 nm may account for the apparently superior penetration of the ofdi system to the sd - oct system with a comparable sensitivity . with the three - dimensional tomographic data of the eye &# 39 ; s posterior segment , the pixel values along the entire depth axis can be integrated to produce a two - dimensional fundus - type reflectivity image . fig6 a shows an exemplary integrated reflectivity image generated from the entire ofdi image sequence shown in fig4 , with the image being two - dimensional reflectance image ( 5 . 3 × 5 . 2 mm 2 ) obtained with the conventional full - range integration method . the exemplary image shows the exemplary optical nerve head , fovea , retinal vessels , and an outline of the deep choroidal vasculature . however , the depth information is not indicated . to address this deficiency of the image generated by a conventional method , it is possible to integrate only selective regions according to using the exemplary embodiment of the system , process and arrangement of the present invention . for example , according to one exemplary embodiment of the present invention , in order to visualize the retinal vasculature with a maximum contrast , it is possible to integrate the reflectivity in the range between iprl and rpe 260 , 270 as shown in fig6 b . this figure shows an illustration of an exemplary embodiment of a axial - sectioning integration technique for producing fundus - type reflectivity images . the shadow or loss of signal created by the retinal vessels above can appear most distinctly . integrating over the entire retina including the vessel often results in a lower contrast in the vasculature because retinal blood vessels produce large signals by strong scattering . automatic image processing conveniently allowed for automatic segmentations of the iprl and rpe layers 260 , 270 . fig6 c depicts an exemplary reflectivity image ( shadow ) of a blood vasculature ( 3 . 8 × 5 . 2 mm 2 ) of the retina vessels . using the thin integration region below the rpe , it is also possible to obtain fundus - type reflectivity images of the choriocapillary layer containing abundant small blood vessels and pigment cells obtained from an upper part of the choroid , as shown in fig6 d . to obtain an image of the complete choroidal region , it is possible to utilize an integration range indicated by references 280 and 290 of fig6 b . the choroidal vasculature is shown in the exemplary resulting reflectivity image of fig6 e which is an exemplary reflectivity image integrated from the center of the choroid revealing the choroidal vasculature . reflectivity images with similar qualities can be obtained from volunteer b . experimental results show that the images generated using the exemplary ofdi techniques at 1050 nm can provide a comprehensive imaging of the human retina and choroid with high resolution and contrast . however , the exemplary embodiment of the ofdi system according to the exemplary embodiments of the present invention may provide an order - of - magnitude higher image acquisition speed than with the use of the conventional time - domain oct systems , and avails the choroid images with an enhanced contrast in comparison to the sd - oct system at 840 nm . the enhanced penetration makes it possible to obtain depth - sectioned reflectivity images of the choroid capillary and vascular networks . fundus camera or scanning laser ophthalmoscope have been conventionally used to view vasculatures . however , such methods may require fluoresce in or indocyanine green angiography to have access to the choroid except for patients with significantly low level of pigmentations . the exemplary ofdi system according to the present invention includes a wavelength - swept laser produced using , e . g ., a commercial soa and custom - built intracavity scanning filter . such laser &# 39 ; s output power , tuning speed and range may yield a sensitivity of about 98 db , a - line rate of 19 khz , and resolution of 10 μm in tissue . increasing the saturation power and gain of soa and reducing the extended - cavity loss can possibly further improve the sensitivity and resolution ( tuning range ). for example , the power exposure level of the exemplary embodiment of the system according to the present invention can be only 550 μw , whereas the maximum ansi limit at 1050 nm is likely to be 1 . 9 mw . fig7 ( a ) shows another exemplary embodiment of a swept laser source arrangement according to the present invention , e . g ., in the 815 - 870 nm spectral range . the swept laser source arrangement can include a fiber - optic unidirectional ring cavity 300 with a free - space isolator 310 . the gain medium 320 may be a commercially - available semiconductor optical amplifier ( e . g ., soa - 372 - 850 - sm , superlum diodes ltd .). an intracavity spectral filter 330 can be provided which may comprise a diffractive grating ( e . g ., 830 grooves / nun ) 332 , two achromatic lenses 334 , 336 in the 4f configuration , and a 72 - facet polygon mirror 340 ( lincoln lasers , inc .). the polygon can be rotated at about 600 revolutions per second to produce unidirectional sweeps from short to long wavelengths at a repetition rate of 43 . 2 khz . the free - space collimated beam in the cavity may have a size of about 1 mm fwhm ( full width at half maximum ). the beam incident angle to the grating normal can be 67 deg . the focal lengths of the two lenses 334 , 336 in the telescope can be 75 ( f 1 ) and 40 ( h ) mm , respectively . it is possible to predict a free - spectral range of 55 nm and fwiim filter bandwidth of 0 . 17 nm . the laser output can be obtained via a 70 % port of a fiber - optic coupler 350 . two polarization controllers 360 , 362 can be used to maximize the output power and tuning range . for example , it is possible to measure the spectral and temporal characteristics of the laser output at a sweep rate of about 43 . 2 khz . the soa may be driven with an injection current of about 110 ma . fig7 ( b ) shows an exemplary output spectrum 380 , 385 measured with an exemplary optical spectrum analyzer in a peak - hold mode at a resolution bandwidth of 0 . 1 nm . the total tuning range is 55 nm from 815 to 870 nm with a fwhm bandwidth of 38 nm . a stability of the output power is provided in the single - shot oscilloscope trace 390 as shown in fig7 ( c ) provided at a about 43 . 2 khz sweep rate and 7 mw averaged power . the peak power variation across tuning cycles may be less than 1 %. the instantaneous laser emission can contain multiple longitudinal modes . an exemplary measurement of the coherence length ( as shown in fig3 ( b )) can indicate that the fwhm line width may be approximately 0 . 17 nm corresponding to the filter bandwidth . the intensity noise characteristic of the laser output may further be characterized by using an electrical spectrum analyzer ( e . g ., model , agilent ) and low - gain silicon detector . the measured relative intensity noise can range from about − 125 db / hz to − 135 db / hz decreasing with the frequency in the frequency range of about 2 mhz to 10 mhz . the noise peaks due to longitudinal mode beating can appear at 91 mhz . the time - average output power may be about 6 . 9 mw . the large output coupling ratio of the exemplary embodiment of the laser source arrangement , e . g ., about 70 %, can ensure that the peak power at the soa does not exceed about 20 mw , e . g ., the specified optical damage threshold of the soa . when this condition is not satisfied , a sudden catastrophic or slowly progressing damage may occur at the output facet of soa chip . increasing the optical damage threshold of the 800 - nm soa chips , e . g ., by new chip designs , can improve the tuning range as well as the long - term reliability . the output may contain a broadband amplified spontaneous emission that can occupy ˜ 8 % ( about 0 . 56 mw ) of the total average power . an exemplary embodiment of the ofdi system according to the present invention can be provided using the exemplary wavelength - swept laser arrangement . the configuration of the exemplary system can be similar to the system shown in fig1 ( b ). the laser output can be split into two paths in an interferometer by a 30 / 70 coupler . in one path ( e . g ., 30 % port , termed “ sample arm ”) may illuminate a biological sample via a two - axis galvanometer scanner ( e . g ., model , cambridge technologies ). the other path , “ reference arm ,” generally provides a reference beam . the signal beam returning from the sample by backscattering is combined with the reference beam at , e . g ., a 50 / 50 coupler , thus producing interference . the interference signal may be detected with a dual - balanced silicon receiver ( e . g ., dc - 80 mhz , 1807 - fs , new focus ). the receiver output is low - pass filtered ( 35 mhz ) and digitized at a sampling rate of 100 ms / s with a 14 - bit data acquisition board ( e . g ., daq , ni - 5122 , national instruments ). a small portion ( 10 %) of the reference beam can be tapped and detected through a grating filter to provide triggers to the daq board . during each wavelength sweep or a - line scan , a large number , e . g ., 2048 samples can be acquired . the sampled data may initially be stored in an on - board memory or on another storage device . upon collecting a desired number of a - line scans , the data set may be transferred to a host personal computer , either to the memory / storage arrangement for on - line processing and / or display or to the hard disk for post processing . when only a single frame is acquired at a time , the exemplary system is capable of processing and displaying the image frame in real time at a frame refresh rate of about 5 hz . for larger data sets , an exemplary 256 mb on - board memory provides for acquisition of up to 65 , 536 a - line scans consecutively for about 1 . 3 sec . this corresponds to about 128 image frames , each consisting of 512 a - lines . post data processing techniques can include reference subtraction , apodization , interpolation into a linear k - space , and dispersion compensation prior to fourier transforms . to characterize and optimize the exemplary embodiment of the system , process and arrangement according to the present invention , it is possible to use an axial point spread function ( or a - line ) by using a partial mirror as the sample (− 50 db reflectivity ). fig8 ( a ) shows a graph 400 of the sensitivity of the exemplary system measured as a function of the reference optical power . the reference power can be varied by using a variable neutral density ( nd ) filter in the reference arm . throughout this measurement , for example , the path length difference between the sample and reference arms may be about 0 . 6 mm , and the optical power returning from the attenuated sample mirror can be 3 . 3 nw at each port of the 50 / 50 coupler . the sensitivity values may be determined by adding the sample attenuation ( e . g ., about 50 db ) to the measured signal - to - noise ratios ( snr ). the reference power can be measured at one of the ports of the 50 / 50 coupler , corresponding to the time - average reference power at each photodiode . at reference powers between about 30 μw and 200 μw , a maximum sensitivity of ˜ 96 db may be obtained . the sensitivity in the unit of decibel may be expressed as : s db = s 0 − 10 log 10 ( 1 + a / p r + p r / b )− δ , where s 0 denotes the shot - noise limited sensitivity , p r is the reference power level , a and b correspond to the reference power levels at which the thermal and intensity noise , respectively , become equal to that of the shot noise in magnitude , and δ can be a fitting parameter associated with other factors contributing to the loss of sensitivity . taking into account amplified spontaneous emission , s 0 may be about 107 db . for example , a = 17 μw from the detector noise level ( e . g ., 3 . 3 pa /√ hz ) and conversion efficiency ( e . g ., 1 a / w ). based on the relative intensity noise of the laser ( e . g ., − 130 db / hz ) and an 18 - db common - noise suppression efficiency of the balanced receiver , b = 280 μw . for example , the best fit to the experimental data 410 of fig8 ( b ) can be obtained with δ = 8 db . fig8 ( b ) shows a graph of the sensitivity 420 measured as a function of depth . this exemplary value may be largely attributed to the simplified model assuming a flat reference spectrum , a polarization mismatch between the sample and the reference light , and the apodization step in data processing , each possibly contributing to a loss of sensitivity by a couple of db &# 39 ; s . due to a finite coherence length of the laser source , the sensitivity can decrease as the interferometric delay increases . it is possible to measure axial point spread functions at various depth locations of the sample mirror by changing the delay in the reference arm while maintaining the reference power at about 100 μw per photodiode , as shown in the graph of fig8 ( b ). for example , each axial profile can be calibrated by measuring the noise floor obtained by blocking the sample arm , and then matching the noise floor to a 50 db level . in this manner , the modest frequency or depth dependence (˜ 2 db ) of the noise floor can be reduced or eliminated . thus , the sensitivity can drop by about 6 db at a depth of about 1 . 9 mm . from a gaussian fit ( dashed line ), the instantaneous laser line width may be about 0 . 17 nm . the fwhm of the axial profile , or the axial resolution in air , can be about 8 μm in the depth from zero to b mm . this corresponds to an axial resolution of ˜ 6 μm in tissue imaging ( e . g ., refractive index , n ≈ 1 . 35 ). as an example , to confirm and demonstrate the capabilities of the exemplary embodiment of the system , process and arrangement according to the present invention for high - speed high - resolution biological imaging , images of xenopus laevis tadpoles may be obtained in vivo by scanning the sample beam ( b - mode scan ). the sample beam can have a confocal parameter of about 250 μm and a fwhm beam size of approximately 7 μm at the focus in air ( n = 1 ). the optical power on the sample may be about 2 . 4 mw . during the imaging procedure , the tadpole ( stage 46 ) can be under anesthesia in a water bath by a drop of about 0 . 02 % 3 - aminobenzoic acid ethyl ester ( ms - 222 ). fig9 shows a sequence of images 450 obtained as the beam is scanned in one dimension repeatedly over the ventricle in the heart . the image sequence was acquired at a frame rate of 84 . 4 hz ( 512 a - lines per frame ) in the duration of 1 . 2 s , but is displayed at a reduced rate of 24 frames per second . each frame , cropped from the original ( 500 × 1024 pixels ), has 400 × 200 pixels and spans a dimension of 3 . 3 mm ( horizontal ) by 1 . 1 mm ( depth , n = 1 . 35 ). the motion of the ventricle including trabeculae can be seen . the ability to image the beating heart with high spatial and temporal resolution may be useful for investigating normal and abnormal cardiac developments in vivo . combined with contrast agents such icg and gold nano particles developed in the 800 - nm region , the exemplary embodiment of the ofdi system , process and arrangement according to the present invention can enable high - speed functional or molecular imaging . an exemplary preferred light source arrangement for ofdi imaging generally has a flat output spectrum . to obtain such desired spectral profile , it is possible to modulate the gain or loss of a gain medium or a filter inside or outside a laser cavity . the filter may be a broadband variable attenuator , and its transmission may be controlled synchronously with laser tuning . the exemplary filter may be a passive spectral filter with a desired transmission spectrum . the gain medium can preferably be a semiconductor optical amplifier , and its gain may be varied by modulating the injection current to the amplifier synchronously with filter tuning . fig1 ( a ) and 10 ( b ) illustrate graphs of exemplary output tuning traces 480 , 490 without and with the use of an exemplary embodiment of a modulation method according to the present invention , respectively . this exemplary method can also be effective to maximize or at least increase the output power and tuning range for a given optical damage threshold of the semiconductor gain chip . the ability to detect and quantify the blood flow in the eye retina and choroid can have impacts in several clinical applications such as for an evaluation of age - related macular degeneration . several methods of extracting the flow information from the phase of the ofdi signals are known in the art . these exemplary conventional methods , however , require a significant beam overlap between two consecutive a - line scans - over sampling , thus causing undesirable compromise between the phase accuracy and image acquisition speed . using the exemplary embodiment of the system , process and arrangement according to the present invention , instead of comparing the phase values of two a - line scans , it is possible to extract multiple phase values corresponding to different time points or wavelengths within a single a - line and compare the values with reference phase values . this exemplary procedure provides for a measurement of the flow velocity at multiple time points during a single a - line scan , permitting a faster beam scan and image acquisition speed . such procedure can be used at decreased phase or velocity measurement accuracy , which is likely to be acceptable in many applications . fig1 illustrates a flow diagram of a conventional method to extract the phase and velocity information from an entire dataset obtained during each wavelength scan . as shown in fig1 , a - line scans , k - th through ( k + 1 )- th are provided . in step 510 , dft from each of such scans is received , and utilized in the formulas a k ( z ) e iφk ( z ) and a k ( z ) e iφk + 1 ( z ) , respectively . then , using the determined results in step 510 , the following determination is made in step 520 : δ ( z )= φ k + 1 ( z )− φ k ( z ). then , in step 530 , a phase image is overlayed to an intensity image if a ( z ) is larger than a particular threshold . here , a m ( z ) denotes the signal amplitude associated with the sample reflectance at a depth z at the m - th a - line scan , φ m ( z ) denotes the signal phase associated with a depth z at the m - th a - line scan , and δ ( z ) represents a difference between the phases . fig1 illustrates a flow diagram of the exemplary embodiment of the process according to the present invention which can be used to obtain the phase and flow information by processing a half of the interference fringe data . for example , similarly to the conventional method shown in fig1 , a - line scans , k - th through ( k + 1 )- th are provided . then , in step 560 , dft from each of such scans is received , and utilized in the following formulas , respectively : a 1 ( z ) iφ1 ( z )− φr , 1 ( z ) , a 2 ( z ) e iφ2 ( z )− φr , 2 ( z ) , etc . using the results obtained from step 560 , the following determination is made in step 570 : δ ( z )= φ 1 ( z )− φ 2 ( z )+ φ r , 1 ( z )− φ r , 2 ( z ). here , a 1 ( z ) and a 2 ( z ) denote the signal amplitudes obtained from the two different portions of the interference signal acquired in each a - line scan , φ 1 ( z ) and φ 2 ( z ) denote the signal phases obtained from the two different portions of the interference signal , and φ r , 1 ( z ) and φ r , 2 ( z ) denote reference phases that may be constants , phases obtained from an auxiliary interferometric signal , or phases associated with a different depth . by subtracting the reference phases from the signal phases , phase noise associated with sampling timing fluctuations and motion artifacts can be greatly reduced . further , in step 580 , a phase image is overlayed to an intensity image if a ( z ) is larger than a particular threshold . this exemplary process can also be applicable to beam - scanning phase microscopy . fig1 ( a ) and 13 ( b ) show exemplary images image of the retina obtained from a healthy volunteer . for example , fig1 ( a ) illustrates a single exemplary image from a large number of frames consecutively acquired using the exemplary embodiment of the system , process and arrangement according to the present invention . the image frame consists of about 1000 axial lines , and the exemplary image shows the fovea and optic disk of the patient . fig1 ( b ) shows an exemplary integrated fundus image produced from multiple cross - sectional images covering an area by integrating the intensity in each depth profile to represent a single point in the fundus image using the exemplary embodiment of the system , process and arrangement according to the present invention . as shown in these figures , the retinal ofdi imaging was performed at 800 - 900 nm in vivo on a 41 - year - old caucasian male subject . the exemplary embodiment of the ofdi system , process and arrangement according to the present invention acquired 23 k a - lines continuously over 1 - 2 seconds as the focused sample beam was scanned over an area including the macular and optic nerve head region in the retina . each image frame was constructed from 1 , 000 a - line scans with an inverse grayscale table mapping to the reflectivity range . the anatomical layers in the retina are clearly visualized and correlate well with previously published oct images and histological findings . the foregoing merely illustrates the principles of the invention . various modifications and alterations to the described embodiments will be apparent to those skilled in the art in view of the teachings herein . indeed , the arrangements , systems and methods according to the exemplary embodiments of the present invention can be used with any oct system , ofdi system , sd - oct system or other imaging systems , and for example with those described in international patent application pct / us2004 / 029148 , filed sep . 8 , 2004 , u . s . patent application ser . no . 11 / 266 , 779 , filed nov . 2 , 2005 , and u . s . patent application ser . no . 10 / 501 , 276 , filed jul . 9 , 2004 , the disclosures of which are incorporated by reference herein in their entireties . it will thus be appreciated that those skilled in the art will be able to devise numerous systems , arrangements and methods which , although not explicitly shown or described herein , embody the principles of the invention and are thus within the spirit and scope of the present invention . in addition , to the extent that the prior art knowledge has not been explicitly incorporated by reference herein above , it is explicitly being incorporated herein in its entirety . all publications referenced herein above are incorporated herein by reference in their entireties .
exemplary apparatus , arrangement and method can be provided for obtaining information associated with an anatomical structure or sample using optical microscopy . a radiation can include first electromagnetic radiation directed to an anatomical sample and at least one second electromagnetic radiation directed to a reference . a wavelength of the radiation can vary over time , and the wavelength can be shorter than approximately 1150 nm . an interference can be detected between third and forth radiations associated with the first , second and fourth radiation , respectively . at least one image corresponding to portion of the sample can be generated using data associated with the interference . source arrangement can be provided which is configured to provide an electromagnetic radiation having a wavelength that varies over time . a period of a variation of the wavelength of the first electromagnetic radiation can be shorter than 1 millisecond , and the wavelength can be shorter than approximately 1150 nm .