Patent Document

CROSS-REFERENCE TO RELATED APPLICATIONS 
     This application is a divisional application of and claims priority to application Ser. No. 10/854,426, filed May 27, 2004, now U.S. Pat. No. 7,697,145 which in turn claims priority to U.S. Provisional Patent Application Ser. No. 60/473,457 filed May 28, 2003, the contents of each of which are hereby incorporated herein by reference. 
    
    
     GOVERNMENT RIGHTS 
     This invention was made with United States Government support under Federal Grant No. BES 0134707 awarded by the National Science. 
    
    
     FIELD OF THE INVENTION 
     The invention relates to imaging systems and more particularly to tomographic and interferometric imaging systems with high resolution. 
     BACKGROUND OF THE INVENTION 
     Optical coherence tomography (OCT) is a method for noncontact optical imaging taking advantage of sequential or scanned distance measurements developed primarily in the 1990&#39;s. In biological and biomedical imaging applications, OCT allows for micrometer-scale imaging noninvasively in transparent and translucent biological tissues. The longitudinal ranging capability of OCT is based on low-coherence interferometry, in which light from a broadband source is split between illuminating the sample of interest and a reference path. The interference pattern of light reflected or backscattered from the sample and light from the reference delay contains information about the location and scattering amplitude of the scatterers in the sample. In conventional (time-domain) OCT, this information is extracted by scanning the reference path delay and detecting the resulting interferogram pattern as a function of that delay. 
     The envelope of the interferogram pattern thus detected represents a map of the reflectivity of the sample versus depth, called an “A-scan”, with depth resolution given by the coherence length of the source. In conventional OCT systems, multiple A-scans are acquired while the sample beam is scanned laterally across the tissue surface, making a continuous series of distance measurements and building up a two-dimensional map of reflectivity versus depth and lateral extent called a “B-scan.” The lateral resolution of the B-scan is given by the confocal resolving power of the sample arm optical system, which is usually given by the size of the focused optical spot in the tissue. 
     Time-domain OCT systems have been designed to operate at moderate (.about.1 image/sec) and high speeds (up to video rate), and have been applied for imaging in biological applications such as imaging of embryonic development, as well as in medical diagnostic applications such as imaging the structures of the anterior and posterior segments of the eye, the skin, the gastrointestinal tract, and other tissues. Specialized probes, endoscopes, catheters, and biomicroscope attachments have been designed to allow for OCT imaging in these applications. 
     The time-domain approach in conventional OCT has been by far the most successful to date in supporting biological and medical applications, and all in-vivo human clinical trials of OCT to date have utilized this approach. However, the time-domain approach in OCT suffers from some limitations. First, the requirement for mechanical scanning, such as with bulk optics, of the reference delay in conventional OCT introduces complexity, expense, and reduced reliability, especially those which image at high speed and acquire A-scans at kilohertz rates. The mechanical scanning reference delay line is typically the most complex optical apparatus in high-speed conventional OCT systems, and can be quite bulky as well. Second, since conventional OCT images are built up serially using a single detector and collecting one pixel of image information at a time, no advantage is taken of modern 1D and 2D array detection technologies which dominate other forms of optical imaging. 
     The serial collection or scanning approach of time-domain OCT is also very wasteful of sample arm light, in that an entire column of pixels is illuminated by that light while reflected light is only collected from one pixel at a time. This wastefulness of sample arm light is costly because sources of broadband light suitable for use in OCT systems are typically expensive and limited in their output power capability, and also because optical damage to tissue structures often limits the maximum power which may be used in OCT imaging, particularly in the retina. Where there is a limit on the amount of light which may be used to illuminate the sample, the wastefulness of sample arm light translates directly into increased image acquisition time. Further, the serial scanning approach in conventional OCT requires that the sample under investigation remains stationary during the acquisition of each A-scan, otherwise motion artifacts may appear in the image. Finally, primarily because of the requirement for a mechanical delay scan, conventional high-speed OCT systems are typically expensive, bulky, and require frequent optical alignment. 
     A potential solution to this need for a new approach has been variously termed spectral radar, Fourier-domain OCT (FDOCT), complex Fourier OCT, Optical Frequency-domain imaging, and swept-source OCT. In FDOCT, a different form of low-coherence interferometry is used in which the reference delay is fixed (except for potential wavelength-scale delay modulation in some implementations), and information about the location and amplitude of scatterers in the sample is derived from the optical spectrum of the light returning from the sample and mixing with the reference. This spectral information is typically acquired by spectrally dispersing the detector arm light using a spectrometer and detecting it with an array detector such as a charge-coupled device (CCD), or else by using a single detector and sweeping the source frequency as a function of time 
     The A-scan data collected using FDOCT can be shown to be related (see below) to the inverse Fourier transform of the spectral data thus acquired. Initial implementations of FDOCT suffered from image artifacts resulting from: 1) large direct-current (DC) signals appearing on the detector array arising from non-interfering light returning from the reference delay and the sample, thus dwarfing the much smaller interferometric signals; and 2) autocorrelation of light signals between different reflections within the sample. As a result, initial results of FDOCT imaging were filled with artifacts and were not comparable to images obtained with time-domain OCT. 
     Recently, newer implementations of FDOCT have appeared which take advantage of techniques well known from phase-shifting interferometry (PSI) to eliminate the sources of both of the artifacts mentioned above. Since both artifacts resulted from light appearing on the detector array which does not arise from interference between sample and reference arm light, the recently introduced technique of complex FDOCT eliminates these artifacts by acquiring multiple spectra with different phase shifts introduced into the reference delay path. 
     In a simple implementation of FDOCT. the reference delay consists of a mirror mounted on a piezoelectric actuator (PZT). One spectrum is acquired at a given position of the mirror, and then another is acquired with a path-length delay of .π/2 (resulting in a round-trip phase shift of π) introduced into the reference arm by the PZT. It is straightforward to show that this π phase shift reverses the sign of the interferometric light components but has no effect on the DC components of the detector arm light, so subtracting the spectra obtained at 0 and π phase shifts results in a spectrum free of DC artifacts. This spectrum can be considered the real part of the complex Fourier transform of the A-scan. Thus, taking the inverse Fourier transform reconstructs the original A-scan. However, since only the real part of the complex Fourier spectrum is acquired, the A-scan data reconstructed is restricted to be symmetric. Specifically, f(−z)=f*(z), and thus only A-scan data for positive displacements (i.e., z&gt;0) can be reconstructed. 
     As a further refinement of this phase-shifting technique, an additional spectrum may be acquired for a path-length delay of π/4 (corresponding to a round-trip phase shift of π/2). This spectrum (also optionally corrected for DC components by division by one of the other spectra or by subtraction with a spectrum acquired with a path-length delay of 3π/4) may be considered the imaginary part of the complex Fourier transform of the A-scan. Thus, taking the inverse Fourier transform of the complete complex spectrum (resulting from all two, three, or four phase measurements) allows for unambiguous reconstruction of all depths in the sample limited only by spatial sampling considerations. Additional refinements to this approach may be applied which are commonplace in phase-shifting interferometry, such as the use of additional phase delays for increased accuracy in measuring the complex spectrum. 
     Complex FDOCT thus addresses several of the needs for OCT systems with decreased complexity and cost and increased reliability, having a mostly fixed reference delay and utilizing an array detector. However, serious limitations to these prior art complex FDOCT implementations include: 1) a means is still required for displacing the reference delay by distances on the scale of a wavelength; all prior systems perform this function by using bulk optical devices outside of the reference arm optical fiber; and 2) the spectra obtained at different reference phases are obtained sequentially, thus the sample and reference arms must be maintained interferometrically motionless during the entire A-scan spectrum acquisition. 
     SUMMARY OF THE INVENTION 
     An object of the invention is to solve at least the above problems and/or disadvantages and to provide at least the advantages described hereinafter. 
     Another object of the invention is to provide an approach to OCT which eliminates the need for a mechanically scanned reference delay and makes use of array detection technologies to acquire signals from all illuminated axial pixels of an A-scan simultaneously. 
     Another object of the invention is to enable the construction of OCT systems which are inexpensive, compact, and are mechanically stable such that they rarely require optical realignment. 
     Another object of the invention is to provide an improvement to FDOCT which does not require any means for modulation of the reference arm path length, or may accomplish such modulation within the existing reference arm optical fiber. 
     Another object of the invention is to provide an FDOCT system which obtains the multiple phase delays required for elimination of image artifacts and/or removal of constraints on A-scan asymmetry simultaneously, thus relaxing constraints on sample and reference motion during A-scan acquisition. 
     To achieve the aforementioned objects, an improved system for FDOCT is provided which implements readout of multiple reference phases in two or more detector channels simultaneously. 
     To further achieve the aforementioned objects, an improved system for FDOCT is provided which eliminates the need for a mechanically scanned reference delay and makes use of array detection technologies or wavenumber swept sources to acquire signals from all illuminated axial pixels of an A-scan simultaneously. 
     To further achieve the aforementioned objects, a method is provided which takes advantage of inherent π phase differences between different ports of interferometers, and which also utilizes orthogonal polarization channels within the reference delay to encode arbitrary phase delays is provided. 
     To further achieve the aforementioned objects, a system is provided that utilizes photodiode arrays for optimal S/N ratio in FDOCT. 
     To further achieve the aforementioned objects, a system is provided that utilizes silicon-based photodiode arrays for FDOCT in the 830 nm OCT window and InGaAs arrays for FDOCT in the 1310 nm and 1550 nm spectral regions. Further advantages of the use of dual-stripe and two-dimensional CCD and photodiode arrays are also disclosed. 
     Additional advantages, objects, and features of the invention will be set forth in part in the description which follows and in part will become apparent to those having ordinary skill in the art upon examination of the following or may be learned from practice of the invention. The objects and advantages of the invention may be realized and attained as particularly pointed out in the appended claims. 
    
    
     
       BRIEF DESCRIPTION OF THE DRAWINGS 
       The invention will be described in detail with reference to the following drawings in which like reference numerals refer to like elements wherein: 
         FIG. 1A  is a schematic illustration of a first embodiment of a FDOCT system, in accordance with the present invention; 
         FIG. 1B  is a schematic illustration of a second embodiment of a FDOCT system, similar to the embodiment of  FIG. 1 , that utilizes a support frequency source, in accordance with the present invention; 
         FIG. 2  is a schematic illustration of a third embodiment of a FDOCT, system in accordance with the present invention; 
         FIG. 3  is a schematic illustration of a fourth embodiment of a FDOCT system, in accordance with the present invention; 
         FIG. 4  is a schematic illustration of a fifth embodiment of a FDOCT system, in accordance with the present invention; 
         FIG. 5  is a schematic illustration of a sixth embodiment of a FDOCT system, in accordance with the present invention; 
         FIG. 6  is a schematic illustration of a seventh embodiment of a FDOCT system, in accordance with the present invention; 
         FIG. 7  is a generalized schematic illustration of a eighth embodiment of a FDOCT system, in accordance with the present invention; and 
         FIG. 8  is a schematic illustration of an imaging spectrometer, in accordance with the present invention. 
     
    
    
     DETAILED DESCRIPTION OF THE INVENTION 
     Referring to  FIG. 1A , a first FDOCT  10  in accordance with one embodiment of the present invention, is shown. The FDOCT  10  of  FIG. 1A  includes an optical circulator  34  with three ports  34   a ,  34   b  and  34   c , and a first fiber coupler  36  having four Michelson interferometer ports  37   a ,  37   b ,  37   c  and  37   d . The optical circulator  34  and the first fiber coupler  36  together make up an optical manipulator  1 . The first fiber coupler  36  is coupled to a first polarization controller  42  by a single mode (SM) optical fiber  41 . The first polarization controller  42  is coupled to a first phase modulator  44  by a SM optical fiber  48 . The first phase modulator  44  is coupled to a SM optical fiber  51  which terminates in a reflector  46 . Together the first polarization controller  42 , first phase modulator  44  and reflector  46 , plus SM optical fibers  48  and  46 , form a reference arm. 
     A second polarization controller  54  is coupled by a SM optical fiber  52  to the first fiber coupler  36 . The second polarization controller  54  is optically coupled to a first lens  56  by a SM optical fiber  65 . The first lens  56  is configured to capture a signal exiting the SM optical fiber  65 , and direct the signal to scanning optics  58 , preferably a moveable mirror. The scanning optics  58 , together with second lens  61 , directs the signal onto a sample  62  and receive a reflected signal therefrom. The second polarization controller  54 , first lens  56 , scanning optics  58 , and second lens  60 , a SM optical fiber  52  and SM optical fiber  65  form a sample arm. Applicant notes that the terms “signal,” “beam,” and “light” are used synonymously to include all forms of electromagnetic radiation suitable for use in imaging systems. 
     Also connected by a SM optical fiber  64  to the first fiber coupler  36  is a first detector  66  having a first spectrometer  66   a  and first array detector  66   b . A second detector  71  is coupled to the optical circulator  34  by a SM optical fiber  68 . The optical circulator  34  may additionally be configured to receive a signal from a source  72  through a SM optical fiber  74 . The first and second detectors,  66  and  71 , and SM optical fibers  64  and  68  together form a detector portion of the FDOCT  10 . 
     The FDOCT system  10  is preferably implemented using a SM fiber Michelson interferometer illuminated by a broadband short-coherence length light source  72 . Light from the source  72  may be evenly split between sample and reference arms by the first fiber coupler  36 . The sample arm can optionally include a second polarization controller  54  for controlling the polarization state of the optical signal and scanning mirror  58  and lens  61  for scanning and focusing the sample arm signal onto the sample  62 . 
     The reference arm may have a fixed path length, preferably obtained by placing a reflector  46  on the tip of the reference arm fiber  51  (thus eliminating bulk optics entirely in the reference arm and the substantial losses incurred in coupling out of and back into the SM fiber  51 ). 
     The reference arm may also optionally include a first polarization controller  42  for matching the polarization state in the reference arm to that in the sample arm, and may also optionally include a first phase modulator  44  which is capable of selectively causing wavelength-scale variations in the reference delay under user control. The first phase modulator  44  can be placed in the sample arm in this and all subsequent implementations without any loss of functionality. Light from the third port  34   c  of the first circulator  34  and light from the third Michelson interferometer port  37   c  of the fiber coupler  36 , having 180° phase difference between them may be coupled into a pair of detectors,  71  and  66  respectively. Detectors  66  and  71  each preferably include spectrometers  66   a  and  71   a , and array detector,  66   b  and  71   b , respectively. This configuration is designed to place copies of the phase-shifted optical spectrum onto a matched pair of array detectors. 
     The FDOCT  10  of  FIG. 1A  acquires a pair of FDOCT spectra, with .pi. radians phase difference between them, on a pair of array detectors to eliminate most motion artifacts associated with conventional phase-shift interferometry. Spectrometers  66   a  and  71   a , and array detectors  66   b  and  71   b  are preferably matched as closely as possible in their optical and electronic characteristics. This can be accomplished by using spectrometers and detector arrays of matching design. 
     In operation, the FDCOT  10  acquires spectra having a relative phase delay of 180° between them from interferometer ports  37   c  and  3  of the interferometer, and differences the spectra in order to eliminate sample and reference arm DC and sample arm autocorrelation terms. The resulting difference spectrum is inverse Fourier transformed to acquire a one-sided A-scan. Care must be taken to assure that the length of the reference arm is adjusted so that no reflections are observed for z&lt;0. 
     In an alternative mode of operation, the FDOCT  10  acquires a 180.degree. relative phase delay between them and differences them in order to eliminate most sample and reference arm DC and sample arm autocorrelation terms, as designated above. The first phase modulator  44  in the reference arm is then adjusted for 90° of additional reference delay. Simultaneous spectra having 90° and 270°. phase delay between them are then acquired and differenced in order to eliminate most sample and reference arm DC and sample arm autocorrelation terms. The first and second difference spectra may then be taken as the real and imaginary parts, respectively, of the complex Fourier transform of the two-sided A-scan. An inverse Fourier transform may be performed on the complex data to obtain the A-scan free of symmetry considerations. Additional phase delays of the first phase modulator  44  may also be selected, and orthogonal pairs of spectra obtained, according to established algorithms for phase-shift interferometry. 
       FIG. 1B  shows a second FDOCT  15 , in accordance with a second embodiment of the present invention. The FDOCT  15  fifteen of  FIG. 1B  is similar to the FDOCT system  10  of  FIG. 1A , except that a swept-frequency source  720  is used in place of the broadband short-coherence length light source  72  of  FIG. 1A . In addition, single-channel detectors  800 A and  800 B are used in place of the spectrometer/array detector combinations of  FIG. 1A . 
     The swept-frequency source  720  is preferably a narrowband light source whose frequency can be swept as a function of time. In the embodiment of  FIG. 1B , the spectrum of the interferometer output(s) is obtained by monitoring the output of the detectors  800 A,  800 B as a function of time while the frequency of the swept-frequency source  720  is swept. 
     The additional embodiments discussed below will be shown with a broadband light source, and with spectrometer/array detector(s) that are used to resolve the spectrum of the interferometer output. However, it should be appreciated that all of the embodiments described below can also be implemented in a swept-source configuration, such as the configuration shown in  FIG. 1B , by replacing the broadband source with a swept-frequency narrowband source, and by replacing each detector with a single-channel time-resolved detector. When Fourier Domain OCT is performed using a swept-source implementation, then all of the same advantages conferred by obtaining multiple simultaneous phase differences, either from multiple output ports of the various interferometer topologies, from polarization encoding of phase in the interferometer arms, or a combination of both approaches, will apply. 
       FIG. 2  shows a second FDOCT embodiment  20 , in accordance with the present invention. Similar to the FDOCT embodiment  10  shown in  FIG. 1A , the FDOCT embodiment  20  of  FIG. 2  has a fiber coupler  36  connected to a first polarization controller  42  by a SM optical fiber  41 . The first polarization coupler  42  is connected to a phase modulator  44  by a SM optical fiber  48 . The phase modulator  44  has a fiber  51  extending therefrom terminating in a reflector  46 . Additionally, the first fiber coupler  36  is connected to a second polarization controller  54  by a SM optical fiber  52 . The second polarization controller  54  is optically coupled to a first lens  56  by a SM optical fiber  64 . The first lens  56  directs an optical output signal from fiber  64  to scanning optics  58 . Scanning optics  58  and lens  61  direct the optical signal to sample  62 . Reflected optical signals from the sample  62  are coupled back into fiber  64  via lens  61  scanning optics  58  and lens  56 . 
     The first fiber coupler  36  is also connected to a first detector  66  by a SM optical fiber  64 . In a variation from the first FDOCT embodiment  10 , the first fiber coupler  36  is connected to a second fiber coupler  76  through a SM optical fiber  38 . The second fiber coupler  76  is connected to a second detector  71  through a SM optical fiber  68 , and includes a 0.degree. port  75  and a 180.degree. port  77 . The second fiber coupler  76  also includes a SM optical fiber stub  78  connected to the 180°. port  77 . A low coherence source  72  may also be connected to the second fiber coupler  76  through a SM optical fiber  74 . 
     The FDOCT embodiment  20  of  FIG. 2  is similar in many respects to the FDOCT embodiment  10  of  FIG. 1A , except that a second fiber coupler  76  is used in the source arm to provide one of the orthogonal phase components, in place of the first circulator  34  of  FIG. 1A . Use of a second fiber coupler  76  may be preferable for decreasing system cost or if circulators are not available to meet the specified wavelength or bandwidth requirements. The penalty for use of the second fiber coupler  76  in place of a circulator will result in a higher insertion loss (3 dB for a fiber coupler versus −0.7 dB for a circulator) in the forward direction, plus a 3 dB loss in the reverse direction of the 0.degree. port  75 , which will need to be matched by an equal amount of attenuation of the 180.degree. port  64  in order to match DC levels on the detectors  66  and  71 . 
     Thus, the FDOCT embodiment  20  may experience a total loss of source light of approximately 6 dB loss (not counting circulator insertion losses) as compared to the FDOCT embodiment  10 . As in the FDOCT embodiment  10  of  FIG. 1A , the separate spectrometers  66   a  and  71   a , and array detectors  66   b  and  71   b  of the first and second detectors  66  and  71  could be replaced by an imaging spectrometer and a dual-row or three-color detector array. Also, any of the three modes of operation discussed in connection with the FDOCT embodiment  10  of  FIG. 1A  may also be used in the FDOCT of  FIG. 2 . 
       FIG. 3  illustrates a third FDOCT embodiment  30 , in accordance with the present invention. Similar to the FDOCT embodiments  10  and  20  discussed above, the FDOCT embodiment  30  includes a fiber coupler  36  coupled to a second polarization controller  54  through a SM optical fiber  52 . The first fiber coupler  36  includes interferometer ports  37   a ,  37   b ,  37   c  and  37   d . The second polarization controller  54  is optically coupled to a first lens  56  through a SM optical fiber  56 . The first lens  56  directs and receives signals to and from a sample  62  through scanning optics  58  and second lens  61 . 
     Also attached to the first fiber coupler  36  is a reference arm including a second phase modulator  84  connected to the first fiber coupler  36  with a SM optical fiber  82 . The second phase modulator  84  is connected to a third polarization controller  88  with a SM optical fiber  86 . The third polarization controller  88  is connected to a third fiber coupler  94  through a SM optical fiber  92 . The third fiber coupler  94  is also connected to the first fiber coupler  36  with a SM optical fiber  96 . The third fiber coupler  94  is connected to a first detector  66  and a second detector  71  through SM optical fibers  64  and  68 , respectively. The FDOCT embodiment  20  of  FIG. 2  may also include a source  72  coupled to the first fiber coupler  36  through a SM optical fiber  75 . 
       FIG. 3  illustrates a FDOCT embodiment  30 , in accordance with the present invention, which takes advantage of the intrinsic phase difference between interferometer ports  37   a  and  37   b  of the first fiber coupler  36 , but has a transmissive reference delay rather than a reflective one. Other aspects of the FDOCT embodiment  30  are similar to the previously discussed FDOCT embodiments  10  and  20 . The FDOCT embodiment  30  of  FIG. 3  may experience a loss of 3 dB of the sample arm reflected light (which is returned into the source). However, this 3 dB loss is less than the corresponding configurations in other FDOCT embodiments, and is approximately the same loss experienced by time-domain OCT in a conventional Michelson interferometer. Thus, the FDOCT embodiment  30  of  FIG. 3  is the preferred implementation when a circulator is unavailable or undesirable. As in the previously discussed FDOCT embodiments  10  and  20 , optimally the first and second spectrometers  66   a  and  71   a  and first and second array detectors  66   b  and  71   b  could be replaced by an imaging spectrometer and a dual-row or three-color detector array. Also, any of the three modes of operation discussed above in connection with FDOCT embodiments  10  and  20 , may also be used. 
       FIG. 4  illustrates a fourth FDOCT embodiment  40 , in accordance with the present invention. The FDOCT embodiment  40  includes a first fiber coupler  36  which is coupled to a first polarization controller  42  by a SM optical fiber  41 . The first fiber coupler  36  has four interferometer ports  37   a ,  37   b ,  37   c , and  37   d . One interferometer port  37   a  is coupled to a first polarization controller  42  by a SM fiber  41 , and the second interferometer port  37   b  is coupled to a second polarization controller  54  by a SM fiber  52 . The first polarization controller  42  is coupled to a first phase modulator  44  by a SM optical fiber  48 . The second polarization controller  54  is coupled to the first fiber coupler  36  by a SM optical fiber  52 , and to a second circulator  102  by a SM optical fiber  64 . The second circulator  102  has a SM optical fiber  110  optically coupled to a first lens  56 , which directs and receives a signal to and from a sample  62  through scanning optics  58  and second lens  61 . The second circulator  102  is also coupled to a fourth fiber coupler  98  through a SM optical fiber  104 . The first phase modulator  44  is also coupled to the fourth fiber coupler  98  by a SM fiber  50 . 
     The fourth fiber coupler  98  is coupled to first and second detector  66  and  71  through SM optical fibers  64  and  68 , respectively. The FDOCT embodiment  40  may also include a first source  72  coupled to the first fiber coupler  36  through a SM optical fiber  74  and a second source  106  coupled to the fiber coupler  36  through a SM optical fiber  108 . 
     The FDOCT embodiment  40  of  FIG. 4  takes advantage of the intrinsic phase difference between interferometer ports  37   a  and  37   b , and also has a transmissive delay. However, the FDOCT embodiment  40  uses a second circulator  102  to direct light onto the sample  62 . The FDOCT embodiment  40  also places the second circulator  102  within one of the arms of the interferometer, where chromatic and polarization mode dispersion effects within the second circulator  102  may be problematic. 
     However, the embodiment  40  makes highly efficient use of source light (except for insertion losses in the circulator  102  itself), and also allows for the introduction of a second source  106 . This may be preferable in order to increase the power of low-coherence light on the sample  62  from available light sources  72  and  106 , and also may be used to increase the bandwidth of illumination by using sources with displaced center wavelengths. As in the previously discussed FDOCT embodiments  10 ,  20  and  30 , the separate spectrometers  66   a  and  71   a  and array detectors  66   b  and  71   b  could be replaced by an imaging spectrometer and a dual-row or three-color detector array. Also, any of the three modes of operation discussed above in connection with the previously discussed FDOCT embodiments  10 ,  20  and  30  may be used in the FDOCT embodiment  40  of  FIG. 4 . 
     All the FDOCT embodiments discussed above may take advantage of the intrinsic .pi. phase delay which is found between output ports of Michelson and Mach-Zehnder interferometers. As described above, this phase delay may be used to simultaneously obtain pairs of spectra which may be differenced to remove non-interferometric noise from the spectral data. However, it also may be desirable to obtain pairs of spectra with .pi./2 phase delay simultaneously, to allow for both removal of non-interferometric noise and also for unambiguous calculation of sample reflectivity without symmetry artifacts. The embodiments described below take advantage of polarization to encode arbitrary phase delays into spectra which may be measured simultaneously. 
       FIG. 5  illustrates a fifth FDOCT embodiment  50 , in accordance with the present invention. The FDOCT embodiment  50  includes a non-polarizing beam splitter  114  optically coupled to a λ./n waveplate  116  and a fixed reference mirror  118 . The non-polarizing beam splitter  114  is also optically coupled to a sample  62  through scanning optics  58  and second lens  61 . The non-polarizing beam splitter  114  is additionally optically coupled to a polarizing beam splitter  120 . Polarizing beam splitter  120  is optically coupled to a first detector  66  through lens  122 , and a second detector  121  through lens  124 . The FDOCT embodiment  50  may also include a source  72  optically coupled to the non-polarizing beam splitter  114  through a polarizer  112 . 
     The FDOCT embodiment  50  is similar to a bulk-optic Michelson interferometer which may encode a 90.degree. phase shift into two polarization channels, which are separated outside of the interferometer by the polarizing beam splitter  120 . The two polarization channels may be directed into a matched pair of spectrometers  66   a  and  71   a  and array detectors,  66   b  and  71   b . Light emitted from the preferably low-coherence source  72  may be linearly polarized at 45.degree. from the vertical by a polarizer  112  placed in the source arm. The non-polarizing beamsplitter  114  splits this light evenly between sample and reference arms. A λ/n. waveplate  116  (for n=2, 4, 8, etc.) may be placed in the reference arm, with its fast axis oriented vertically (i.e., at 0.degree. to the vertical). 
     Thus, the horizontal component of the light in the reference arm may experience a phase delay of 4π/n radians with respect to the vertical component after double-passing the λ/n waveplate  116 . These two components may be separated by the polarizing beamsplitter  120  in the detector arm, which sends the phase-delayed components of the reference, arm light, along with an equal division of the light reflected from the sample  62 , into a matched pair of spectrometers  66   a  and  71   a , and array detectors,  66   b  and  71   b.    
     For example, for n=8, i.e. an eighth-wave plate in the reference arm, there will be a λ/4 or 90° phase difference between the spectra obtained from the reference and sample arms, which is sufficient for unambiguous reconstruction of the sample reflectivity from the complex spectrum thus obtained. For other values of n, i.e., n=4 (quarter-wave plate), n=2 (half-wave plate), other phase delays between the collected spectra may also be obtained as needed for various phase-shift interferometry reconstruction algorithms. Although only 2 phase delays may be encoded into polarization, the polarization-based approach of the FDOCT embodiment  50  may be combined with the intrinsic interferometer port phase difference methods of the other FDOCT embodiments discussed above to obtain at least 4 simultaneous spectra with different phase delays. 
     As another example, the addition of a circulator into the source arm of the FDOCT embodiment  50 , which may direct light into another polarizing beamsplitter and two more spectrometers, would allow for the simultaneous acquisition of spectra having 0°, 90°, 180°, and 270° phase differences. It will be clear to one of ordinary skill in the art that numerous other implementations of the inventive concept of polarization encoding of phase may be used as extensions of the FDOCT embodiment  50 , such as the rotation of all polarization-sensitive elements in the embodiment  50  by a fixed angle, or numerous alternative placements of the polarization-sensitive elements (including placing of the λ/n plate  116  in the sample arm instead of the reference arm), while still falling within the scope of the present invention. 
     Modes of operation of the FDOCT embodiment  50  of  FIG. 5  includes acquiring simultaneous spectra having 0° and 180° phase delay by use of a λ/4 waveplate in the reference arm. The spectra may be differenced in order to eliminate sample and reference arm DC and sample arm autocorrelation terms. The resulting difference spectrum may be inverse Fourier transformed to acquire a one-sided A-scan. The length of the reference arm is preferably adjusted so that no reflections are observed for z&lt;0. 
     Another mode of operation for use with the FDOCT embodiment  50  of  FIG. 5  includes acquiring simultaneous spectra having 0° and 90° phase delay between them and differencing them in order to eliminate sample and reference arm DC and sample arm autocorrelation terms. These spectra may be taken as the real and imaginary parts, respectively, of the complex Fourier transform of the two-sided A-scan. The inverse Fourier transform may then be performed on the complex data to obtain the A-scan free of symmetry considerations. 
     Another mode of operation for use with the FDOCT embodiment  50  of  FIG. 5  includes acquiring simultaneous spectra having 0°, 90°, 180°, and 270° phase difference between them, by use of a combination of polarization encoding of phase and intrinsic phase delay between interferometer ports, as described above. Pairs of spectra having 180° phase delay between them may be differenced in order to eliminate sample and reference arm DC and sample arm autocorrelation terms. The differenced pairs of spectra may then be taken as the real and imaginary parts, respectively, of the complex Fourier transform of the two-sided A-scan. The inverse Fourier transform may be performed on the complex data to obtain the A-scan free of symmetry considerations. 
       FIG. 6  illustrates a sixth FDOCT embodiment  60 , in accordance with the present invention. The FDOCT embodiment  60  includes a first fiber coupler  36  coupled to a first polarization controller  42  through a SM optical fiber  41 . The first polarization controller  42  is coupled to a SM optical fiber  51 , which terminates in a reflector  46 . The first fiber coupler  36  is also coupled to a second polarization controller  54  through a SM optical fiber  52 . The second polarization controller  54  is optically coupled to a first lens  56  through a SM optical fiber  64 . The first lens  56  is optically coupled to a sample  62  through a scanning optics  58  and second lens  61 . The first fiber coupler  36  is also coupled to a third lens  126  through a coupler  64 . The third lens  126  is optically coupled to a polarizing beam splitter  120 . The polarizing beam splitter  120  is optically coupled to a lens  122  and a first detector  66 . The polarizing beam splitter  120  is also optically coupled to a lens  124  and a second detector  71 . 
     It is preferable to have the capability for arbitrary simultaneous dual phase delays between acquired spectra in a fiber interferometer, since most practical OCT systems to date make use of the flexibility of fiber optic systems for medical and biological applications. The FDOCT embodiment  60  illustrates one possible implementation of a fiber-optic interferometer for imaging, which uses polarization for phase encoding. In this embodiment, the light source  72  is either polarized or a polarization element  112  (such as a fiber polarizer) is used in the source arm. Preferably, the interferometer is constructed from polarization-maintaining fiber (PMF), although previous work in polarization-sensitive OCT has shown that non-PMF fiber is also capable of maintaining phase relationships between orthogonal polarization states propagating through the fiber. In the FDOCT embodiment  60  of  FIG. 6 , a fiber polarization controller  42  in the reference arm may be used to simulate the λ/n waveplate  116  in the FDOCT embodiment  60 , and the second polarization controller  54  in the sample arm may be used to correct for stress-induced birefringence in the sample arm fiber assembly. 
     Although the FDOCT embodiment  60  is just one example of polarization phase encoding in a fiber interferometer, any of the fiber interferometers shown in the FDOCT embodiments described above could be altered to use polarization phase encoding by the addition of a PBS and matched pair of spectrometers to each output port  37   a  and  37   b . Modifications of the FDOCT embodiments described above in this way would result in the simultaneous collection of spectra with 4 phase delays (pairs of which are separated by 180°) since each of those implementations have dual interferometer outputs. 
       FIG. 7  shows a generalized embodiment  100  of a FDOCT system, in accordance with the present invention. The FDOCT  100  includes a signal manipulator  12 . The signal manipulator  12  is coupled to a reference portion  14  by a coupler  20 , and a sample portion  16  by a coupler  22 . The signal manipulator  12  is also coupled to a detector  18  by a coupler  24 . The signal manipulator  12  may also be coupled to a source  26  by a coupler  28 . The sample portion  16  is coupled  31  to a sample  32 . 
     Examples of signal manipulator  12  of  FIG. 7  can include, but are not limited to, the combination of the first optical circulator  34  and the first fiber coupler  36  of  FIG. 1 , the second fiber coupler  76  and first fiber coupler  36  of  FIG. 2 , and the first fiber coupler  36  of  FIGS. 3 and 4 . Additionally, the signal manipulator  12  of  FIG. 7  may also correspond to the polarizer  110  and nonpolarizing beam splitter  114  of  FIG. 5 , and the polarizing element  112  with the fiber coupler  36  of  FIG. 6 . 
     The reference portion  14  of  FIG. 7  may include, but is not limited to, the combined first polarization controller  42 , first phase modulator  44 , and reflector  46  of  FIGS. 1 and 2 . The reference portion  14  of  FIG. 7  may also include, but is not limited to, the second phase modulator  84  and third polarization controller  88  of  FIG. 3 , and the first polarization controller  42  and first phase modulator  44  of  FIG. 4 . The reference portion  14  of  FIG. 7  may also include, but is not limited to, the combination of the λ/n plate  116  and reference mirror  118  of  FIG. 5 , and the first polarization controller  42  and reflector  46  of  FIG. 6 . 
     The sample portion  16  of  FIG. 7  may include, but is not limited to, the second polarization controller  54 , first lens  56 , scanning optics  58  and second lens  61  of  FIGS. 1, 2, 3 and 6 . The sample portion of  FIG. 7  may also include, but is not limited to, the combination of the second polarization controller  54 , second optical circulator  102 , first lens  56 , scanning optics  58  and second lens  61  of  FIG. 4 , and the scanning optics  58  and second lens  61  of  FIG. 5 . 
     The detector  18  of  FIG. 7  may include, but is not limited to, the first detector  66  and second detector  71  of  FIGS. 1 and 2 . The detector  18  of  FIG. 7  may also include, but is not limited to, the combination of the first and second detectors  66  and  71 , and the third fiber coupler  94  of  FIG. 3 , and the first and second detectors  66  and  71 , and the fourth fiber coupler  98  of  FIG. 4 . Finally, the detector  18  of  FIG. 7  may include, but is not limited to, the first and second detectors  66  and  71 , the lens  124  and the lens  122 , and the polarization beam splitter  120  of  FIGS. 5 and 6 , as well as the third lens  126  of  FIG. 6 . 
     It should also be noted that the source  26  shown in  FIG. 7  may include, but is not limited to, the first source  72  of  FIGS. 1, 2, 3, 5 and 6 . The source  26  of  FIG. 7  may also include, but is not limited to, the first source  72  and second source  106  of  FIG. 4 . 
     Referring to  FIG. 8 , a detector  66  with imaging capabilities suitable for use with FDOCT embodiments  10 ,  20 ,  30 ,  40 ,  50 ,  60  and  100  is shown. The detector  66  has dual input fibers  128  and  129  coupled to an input slit  136  of the detector  66 . The detector  66  also includes an output area  130 . The output area includes a first array  132  and a second array  134  which may receive two spectra,  138  and  140 . 
     In operation, the detector  66  receives two multi-frequency signals carried in the dual input fibers  128  and  129 , at the input slit  136 . The input signals preferably have a phase difference between them, and the phase difference is preferably 90 degrees. Each input signal is then dispersed according to frequency and the resulting spectra  138  and  140 , are directed onto the arrays  132  and  134 . The arrays  132  and  134 , may then measure power as a function of frequency for each spectrum  138  and  140 . 
     The previously described FDOCT embodiments  10 ,  20 ,  30 ,  40 ,  50 ,  60  and  100  all preferably take advantage of the detection of multiple simultaneous optical spectra in the detector arm of the interferometer, corresponding to multiple phase-delayed components of a complex FDOCT signal.  FIGS. 1-7  illustrate simple cases of dual-channel detection of spectra separated by orthogonal (90°) or opposite (180°) phase obtained through the use of intrinsic phase delays associate with interferometer ports, or through polarization multiplexing. A combination of intrinsic and polarization-derived phase delays could also be used to obtain at least four simultaneous phase delays, which would preferably be detected in an equal number of spectral channels. Although four or more simultaneous phase delays may be desirable to accommodate some phase-shift interferometry reconstruction algorithms, collection of two simultaneous phases (optimally separated by 90°) would be one preferred embodiment of the invention, as that would allow for almost complete removal of autocorrelation noise and calculation of complex double-sided spectra with the least complexity and expense. 
     The light source  72  in the aforementioned embodiments is preferably a low-coherence source. Multiple light sources  72  and  106 , may also be used. The spectrometers  66  and  71  used in the FDOCT embodiments should preferably be selected for maximum optical throughput and optimal matching of their dispersion to the spectral content of the low-coherence source, to avoid artifacts associated with the spatial frequency response of the array (i.e., the dispersion should be chosen so that the spectrum nearly fills the detector array). Grating spectrometers currently exhibit the optimal combination of characteristics to satisfy these constraints, however other spectrometer types may be used. If space utilization is not a serious constraint, prism-based spectrometers may give better throughput at the cost of increased required path length. 
     Preferably, the detector arrays utilized are photodiode arrays with the maximum well depth available, and optimized for response in the wavelength range of the source. Using current detector array technology, this corresponds to the use of silicon photodiode arrays for the popular 830 nm OCT window and for any other desired OCT spectral windows below approximately 1000 nm, and for InGaAs photodiode arrays for the popular 1310 nm OCT window and for any other desired OCT spectral windows in the near-infrared beyond 1000 nm. Charge-coupled device (CCD) arrays may also be used, however current-generation CCDs utilize silicon substrates and may thus be unsuitable for imaging at the popular OCT wavelengths above 1000 nm. 
     For simplicity,  FIGS. 1-7  above illustrate the phase-delayed spectral channels as being dispersed and detected in separate detectors. As shown in  FIG. 8 , however, the spectrometers and arrays in the detectors shown in each implementation can be replaced by a single imaging spectrometer having a multiple-stripe or two-dimensional detector array, with the input fibers arranged in close vertical proximity to one another so as to have their spectra imaged onto the separate rows (stripes) of the detector array. Such an arrangement would have the significant advantages of allowing for optimal matching of the spectra placed on all channels (since all channels would use the same grating and other spectrometer optics), as well as the cost and space savings achievable by using a single spectrometer. Dual-stripe photodiode arrays have been commercially available in the past, and also three-row CCD arrays designed for 3-color line scanning are currently commercially available. Two of the three rows of a 3-color line scanner array could also be used in place of a dual-row array. 
     For a preferred embodiment of two FDOCT channels separated by 90° or 180°, a single dual-stripe photodiode array mounted onto an imaging spectrometer would be the preferred detector. Alternatively, a two-dimensional CCD or photodiode array could be used to either a) simulate a dual-stripe array by using the binning capabilities of such an array to collect dual simultaneous spectra, or b) collect more than two simultaneous spectra through an appropriate alternative binning algorithm. However, two-dimensional CCDs still have significant well-depth limitations, and large two-dimensional photodiode arrays are not yet commercially available. 
     It should be noted that the term “optical circulator” is used herein to mean any type of device capable of directional coupling of electromagnetic radiation incident on port  1  to port  2 , while simultaneously coupling electromagnetic radiation incident on port  2  to port  3  Also, as used herein, a “fiber coupler” is used to mean any device which receives an input signal of electromagnetic radiation and divides that signal between two output ports. It should be noted that as used herein, a fiber coupler may have multiple ports wherein each port can serve as an input port for a selected pair of output ports as well as function as an output port for a selected input port. The fiber coupler splitting ratio for all embodiments is ideally 50/50, however this splitting ratio may be modified to account for nonideal performance of other components, for example to compensate for the insertion loss of circulators or other elements. “Polarization controller” is used herein to mean any semiconductor or bulk optical device used to selectively manipulate the polarization of an input signal and output the manipulated signal. “Optical fiber” is used to mean any device or set of devices used to direct electromagnetic radiation along a prescribed path. Thus, “optical fiber” can mean a signal strand of optically transparent material bounded by a region of contrasting index of refraction, as well as mirrors or lenses used to direct electromagnetic radiation along a prescribed path. 
     As used herein, “phase modulator” means any semiconductor or bulk device used to modulate or otherwise alter the phase of an input electromagnetic signal and output the manipulated electromagnetic signal. “Reflector” is used herein to mean any device capable of reflecting an electromagnetic signal. Thus, “reflector” can be used to mean a mirror, an abrupt transmission in an index of refraction as well as a periodically spaced array structure such as a Bragg reflector. “Scanning optics”, means any system configured to sweep an electromagnetic signal across a chosen area. 
     “Detector” is used herein to mean any device capable of measuring energy in an electromagnetic signal as a function of wavelength. Additionally, “source” is used to mean any source of electromagnetic radiation, and preferably means a low coherence source of electromagnetic radiation. 
     The foregoing embodiments and advantages are merely exemplary and are not to be construed as limiting the present invention. The present teaching can be readily applied to other types of apparatuses. The description of the present invention is intended to be illustrative, and not to limit the scope of the claims. Many alternatives, modifications, and variations will be apparent to those skilled in the art. In the claims, means-plus-function clauses are intended to cover the structures described herein as performing the recited function and not only structural equivalents but also equivalent structures.

Technology Category: g