Abstract:
Exemplary embodiments of probes, apparatus, systems and methods can be provided which provide at least one electro-magnetic radiation to at least one sample. For example, a plurality of axicon lenses can be provided which are configured to provide the electro-magnetic radiation(s) having at least partially annulus shape. In addition or alternatively, at least one optical arrangement can be provided which is configured to forward at least one radiation to the sample therethrough having at least partially circularly-symmetric pattern. For example, at least one first portion of the radiation transmitted through a circular section of the pattern can have an optical path-length that is different from an optical path-length of at least one second portion of the radiation transmitted through at least one other section of the pattern.

Description:
CROSS-REFERENCE TO RELATED APPLICATION(S) 
     This application is based upon and claims the benefit of priority from U.S. Patent Application Ser. Nos. 61/311,171 and 61/311,272, both filed Mar. 5, 2010, the entire disclosures of which are incorporated herein by reference. 
    
    
     FIELD OF THE DISCLOSURE 
     The present disclosure relates to exemplary embodiments of imaging systems, apparatus and methods, and more specifically to methods, systems and computer-accessible medium which provide microscopic images of at least one anatomical structure at a particular resolution. 
     BACKGROUND INFORMATION 
     Coronary artery disease (CAD) and its clinical manifestations, including heart attack or acute myocardial infarction (AMI), is the number one cause of mortality in the US, claiming nearly 500,000 lives and costing approximately $400 B per year. Topics relevant to the pathophysiology of CAD, such as the development and progression of coronary atherosclerotic lesions, plaque rupture and coronary thrombosis, and the arterial response to coronary device and pharmacologic therapies are therefore of great significance today. These biological processes can be mediated by molecular and cellular events that occur on a microscopic scale. Certain progress in understanding, diagnosing, and treating CAD has been hindered by the fact that it has been difficult or impossible to interrogate the human coronary wall at cellular-level resolution in vivo. 
     Over the past decade, intracoronary optical coherence tomography (OCT) has been developed, which is a catheter-based technique that obtains cross-sectional images of reflected light from the coronary wall. Intracoronary OCT has a spatial resolution of 10 μm, which is an order of magnitude better than that of the preceding coronary imaging method, intravascular ultrasound (IVUS). In the parent R01, a second-generation form of OCT has been developed, i.e., termed optical frequency domain imaging (OFDI), that has very high image acquisition rates, making it possible to conduct high-resolution, three-dimensional imaging of the coronary vessels. In addition, a flushing method has been developed which, in combination with the high frame rate of OFDI, can overcome at least some of the obstacles of blood interference with the OCT signal. As a direct result, it may be preferable to perform intracoronary OCT procedures in the clinical setting. Indeed, certain interventional cardiology applications for OCT have emerged, and growing the field exponentially. It is believed that OCT can become a significant imaging modality for guiding coronary interventions worldwide. 
     Since the technology developed in the parent R01 has been translated and facilitated for a clinical practice through the distribution of commercial OFDI imaging systems, it may be preferable to review macromolecules and cells involved in the pathogenesis of CAD. 
     For example, a transverse resolution in OCT procedure(s) can be determined by the catheter&#39;s focal spot size. To improve the resolution, it is possible to increase the numerical aperture of the lens that focuses light into the sample. This conventional method, however, neglects the intrinsic compromise between transverse resolution and depth of field in cross-sectional OCT images and results in images in which only a narrow depth range is resolved. 
     An alternative approach can exploit the unique characteristics of Bessel, or “non-diffracting” beams to produce high transverse resolution over enhanced depths-of-field. Bessel beam illumination and detection of light reflected from the sample, however, can suffer from a significant reduction in contrast and detection efficiency. Thus, there may be a need to overcome at least some of the deficiencies associated with the conventional arrangements and methods described above. 
     As briefly indicated herein above, certain exemplary embodiments of the present disclosure can be associated and/or utilize analysis and manipulation of a coherent transfer function (CTF) of an exemplary OCT system. The current invention is instead based on an analysis and manipulation of the coherent transfer function (CTF) of an OCT system. The CTF can be considered a coherent extension of a modulation transfer function (MTF) and an optical transfer function (OTF). Thus, for example, for non-interferometric systems, the MTF or OTF can be manipulated and utilized according to certain exemplary embodiments. In general, the quality of an optical system can be assessed by comparing its transfer function to that of a diffraction-limited optical system.  FIG. 1  shows a graph of coherent transfer functions (CTFs) for, e.g., a diffraction limited 2.5 μm diameter spot and 2.5 μm spot with an extended focal range of 2.0 mm, produced by Bessel beam illumination and detection. As illustrated in  FIG. 1 , the transfer function of a Bessel beam illumination and detection  100  can have spatial frequencies that exceed a diffraction-limited system  110 , although it likely sacrifices low- and mid-range spatial frequencies, possibly resulting in reduced contrast and detection sensitivity. 
     Thus, there may be a need to overcome at least some of the deficiencies associated with the conventional arrangements and methods described above. 
     SUMMARY OF EXEMPLARY EMBODIMENTS OF THE DISCLOSURE 
     To address and/or overcome such deficiencies, one of the objects of the present disclosure is to provide exemplary embodiments of systems, methods and computer-accessible medium according to the present disclosure, which can provide microscopic images of at least one anatomical structure at a particular resolution. Another object of the present disclosure is to overcome a limited depth of focus limitations of conventional Gaussian beam and spatial frequency loss of Bessel beam systems for OCT procedures and/or systems and other forms of extended focal depth imaging. 
     According to another exemplary embodiment of the present disclosure, more than two imaging channels can illuminate/detect different Bessel and/or Gaussian beams. In yet a further exemplary embodiment, different transfer functions can be illuminated and/or detected. The exemplary combination of images obtained with such additional exemplary beams can facilitate the μOCT CTF to be provided to the diffraction-limited case, and can also facilitate a depth-of-field extension even further. 
     Thus, exemplary embodiments of probes, apparatus, systems and methods can be provided which provide at least one electro-magnetic radiation to at least one sample. For example, a plurality of axicon lenses can be provided which are configured to provide the electro-magnetic radiation(s) having at least partially annulus shape. A housing arrangement can be provided which at least partially encloses the axicon lenses. The housing arrangement can be shaped and structured to be inserted into an anatomical structure and/or an endoscope. An optical arrangement can be provided which, when receiving the electro-magnetic radiation(s), generates a further radiation that generates a transfer function of the optical arrangement which is different from the transfer function of at least one of the axicon lenses. A plurality of wave-guiding arrangements can also be provided, one of which can be coupled to at least one of the axicon arrangements, and another one of which can be coupled to the optical arrangement. 
     In another exemplary embodiment, when the first and third radiations impact the optical arrangement(s) having an optical aperture, the resultant respective radiations can be at least partially focused to a depth of focus and/or a focal range that is greater than approximately Raleigh range of a full aperture of illumination. A spot diameter of focus can be less than 10 μm, and the depth of the focus or the focal range can be greater than approximately 1 mm, 0.5 mm, 2 mm, etc. 
     According to yet another exemplary embodiment of the present disclosure, further probes, apparatus, systems and methods can be provided which provide at least one electro-magnetic radiation to at least one sample. For example, at least one optical arrangement can be provided which is configured to forward at least one radiation to the sample therethrough having at least partially circularly-symmetric pattern. For example, at least one first portion of the radiation transmitted through a circular section of the pattern can have an optical path-length that is different from an optical path-length of at least one second portion of the radiation transmitted through at least one other section of the pattern. 
     In a still further exemplary embodiment of the present disclosure  15 , the first and second portions of the radiation(s) can be associated with respective first and second transfer functions that are different from one another. An interferometric arrangement can be provided which includes at plurality of detectors, and each of the detectors can be configured to detect the first transfer function and the second transfer function. When the first and third radiations impact the at least one optical arrangement having an optical aperture, the resultant respective radiations can be at least partially focused to a depth of focus or a focal range that is greater than approximately Raleigh range of a full aperture of illumination. 
     According to a further exemplary embodiment of the present disclosure, a spot diameter of focus can be less than 10 μm, and the depth of the focus or the focal range can be greater than approximately 1 mm, 0.5 mm, 2 mm, etc. The optical arrangement(s) can include a plurality of wave guiding arrangements, and, at a point of emission of each of the wave guiding arrangements, the optical arrangement(s) can causes a phase of each of the electro-magnetic radiation(s) to have a predetermined value. The optical arrangement(s) can include a plurality of axicon lenses which are configured to generate at least one radiation. 
     These and other objects, features and advantages of the exemplary embodiment of the present disclosure will become apparent upon reading the following detailed description of the exemplary embodiments of the present disclosure, when taken in conjunction with the appended claims. 
    
    
     
       BRIEF DESCRIPTION OF THE DRAWING(S) 
       Further objects, features and advantages of the present invention will become apparent from the following detailed description taken in conjunction with the accompanying figures showing illustrative embodiments of the present disclosure, in which: 
         FIG. 1  is an exemplary graph of coherent transfer functions (CTFs) as a function of spatial frequencies produced by the prior Bessel beam illumination and detection; 
         FIG. 2  is an exemplary graph of coherent transfer functions (CTFs) as a function of spatial frequencies produced by an exemplary embodiment of a procedure and/or technique according to the present disclosure; 
         FIG. 3A  is a first exemplary OCT image an exemplary OCT image of a cadaver coronary artery plaque obtained using an exemplary procedure/techniques according to an exemplary embodiment of the present disclosure, whereas an exemplary Gauss-Gauss image contains low spatial frequency information; 
         FIG. 3B  is a second exemplary OCT image of the cadaver coronary artery plaque using an exemplary procedure/techniques according to an exemplary embodiment of the present disclosure, whereas an exemplary Bessel-Bessel image provides high-resolution but loses low and mid spatial frequencies; 
         FIG. 3C  is a third exemplary OCT image of the cadaver coronary artery plaque using an exemplary procedure/techniques according to an exemplary embodiment of the present disclosure, which provides a combined μOCT image (e.g., Gauss−Gauss+Gauss−Bessel+Bessel−Bessel), and images are normalized and displayed with the same brightness/contrast values; 
         FIG. 4  is a side cut-away view of a diagram of the distal optics of a OCT catheter system according to an exemplary embodiment of the present disclosure; 
         FIG. 5A  is an exemplary graph of an illumination profile generated using the distal optics con figuration of the system the exemplary embodiment of shown in  FIG. 4 ; 
         FIG. 5B  is an exemplary graph of simulated x-z PSF generated using the distal optics con figuration of the system the exemplary embodiment of shown in  FIG. 4 ; 
         FIG. 6  is a schematic diagram of a system for generating one or more μOCT images according to still a further exemplary embodiment of the present disclosure; 
         FIG. 7  are side cut-away views of diagrams of the distal optics of the OCT catheter system according to still another exemplary embodiment of the present disclosure which includes axicon pair and a routing of a ring beam and a Gaussian beam of the distal optics configuration; 
         FIG. 8  is a side cut-away view of a diagram of the OCT catheter system according to yet further exemplary embodiment of the present disclosure which includes an exemplary optical pathlength incoding probe configuration that uses a single fiber and a single axicon lens; 
         FIG. 9  are side cut-away views of diagrams of the OCT catheter system according to a still further exemplary embodiment of the present disclosure which includes a further exemplary optical pathlength incoding probe configuration that uses a single fiber and a single axicon lens; 
         FIG. 10  are schematic views of diagrams of the distal optics of the OCT catheter system according to a further exemplary embodiment of the present disclosure which includes a single fiber multifocal lens probe configuration; 
         FIG. 11  is a side cut-away view of a diagram of the OCT catheter system according to a still further exemplary embodiment of the present disclosure which utilizes a mirror tunnel; 
         FIG. 12  is a side cut-away view of a diagram a portion of the OCT catheter system according to yet another exemplary embodiment of the present disclosure which utilizes a reflective achromatic phase mask and a ball lens; 
         FIG. 13  is a graph of a phase shift spectra of chromatic light upon reflection at glass-metal interface based on the exemplary embodiment of  FIG. 12 ; 
         FIG. 14A  is an illustration of a Huygens diffraction pattern of lens with conventional focusing; 
         FIG. 14B  is an exemplary illustration of a Huygens diffraction pattern of lens with reflective achromatic phase mask and ball lens depicted in the exemplary embodiment of the system illustrated in  FIG. 13 . 
         FIG. 15A  is a schematic diagram of an exemplary embodiment of a focusing arrangement that uses a refractive achromatic phase doublet mask in accordance with an exemplary embodiment of the present disclosure; 
         FIG. 15B  is an exemplary graph of transverse phase profiles of an exemplary mask illustrated in  FIG. 15A ; 
         FIG. 16  is a schematic diagram of the OCT system which includes a wavefront beam splitter and a common path interferometer, according to yet another exemplary embodiment of the present disclosure; 
         FIG. 17A  is an exemplary simulated PSF illustration of generated by the exemplary OCT system shown in  FIG. 16  that uses a monochromatic light source (e.g., λ=825 nm) and a spherical aberration free objective lens; 
         FIG. 17B  is an exemplary simulated PSF illustration of generated by the exemplary OCT system shown in  FIG. 16  that uses a monochromatic light source (e.g., λ=825 nm) and an objective lens with a spherical aberration and a wavelength dependent focal shift; 
         FIG. 17C  is an exemplary simulated PSF illustration of generated by the exemplary OCT system shown in  FIG. 16  that uses a broadband source (e.g., about 600 nm to 1050 nm) and an objective lens with spherical aberration and a wavelength dependent focal shift; 
         FIG. 17D  is an exemplary simulated PSF illustration of generated by the exemplary OCT system shown in  FIG. 16  that uses broadband source (e.g., 600 nm to 1050 nm), an objective lens with spherical aberration and a wavelength dependent focal shift, and an wavefront beam splitter; 
         FIG. 18A  is an exemplary μOCT image of a coronary plaque showing multiple leukocytes (arrows); 
         FIG. 18B  is an exemplary μOCT image of a coronary plaque illustrating multiple leukocytes (arrows) of two different cell types, one smaller cell with scant cytoplasm, consistent with a lymphocyte (L) and another, larger cell with a highly scattering cytoplasm, indicative of a monocyte (M); 
         FIG. 18C  is an exemplary μOCT image of a coronary plaque illustrating a cell with an indented, bean-shaped nucleus (M) characteristic of a monocyte; 
         FIG. 18D  is an exemplary μOCT image of a coronary plaque illustrating a leukocyte with a multi-lobed nucleus, which can indicate a neutrophil (N) attached to the endothelial surface; 
         FIG. 18E  is an exemplary μOCT image of the coronary plaque illustrating multiple leukocytes tethered to the endothelial surface by pseudopodia; 
         FIG. 18F  is an exemplary μOCT image of the coronary plaque illustrating cells with the morphology of monocytes (M) in a cross-section and an inset transmigrating through the endothelium; 
         FIG. 18G  is an exemplary μOCT image of multiple leukocytes distributed on the endothelial surface; 
         FIG. 19A  is an exemplary μOCT image of platelets (P) adjacent to a leukocyte characteristic of a neutrophil (N), which is also attached to a small platelet; 
         FIG. 19B  is an exemplary μOCT image of fibrin (F) which is visible as linear strands bridging a gap in the coronary artery wall; 
         FIG. 19C  is an exemplary μOCT image of a cluster of leukocytes (L), adherent to the fibrin in an adjacent site to that illustrated in  FIG. 19B ; 
         FIG. 19D  is an exemplary μOCT image of Fibrin thrombus (T) with multiple, entrapped leukocytes; 
         FIG. 19E  is an exemplary μOCT image of a more advanced thrombus (T) showing a leukocyte and fibrin strands; 
         FIG. 19F  is an exploded view of a portion of the exemplary μOCT image shown in  5   FIG. 19E ; 
         FIG. 20A  is a cross-sectional exemplary μOCT image of endothelial cells in culture; 
         FIG. 20B  is an en face exemplary μOCT image of endothelial cells in culture; 
         FIG. 20C  is an exemplary μOCT image of a native swine coronary artery cross-section; 
         FIG. 20D  is an exemplary three-dimensional rendering of the swine coronary artery, demonstrating endothelial “pavementing”; 
         FIG. 21A  is an exemplary μOCT image of microcalcifications which can be seen as bright densities within the μOCT image of the fibrous cap; 
         FIG. 21B  is an exemplary μOCT image of the microcalcifications which can be seen as dark densities on the corresponding histology; 
         FIG. 22A  is an exemplary μOCT image of a large calcium nodule, demonstrating disrupted intima/endothelium; 
         FIG. 22B  is an expanded view of the region enclosed by a box illustrating microscopic tissue strands, consistent with fibrin (F), adjoining the unprotected calcium (white arrow) to the opposing detached intima; 
         FIG. 22C  is an illustration of a corresponding histology of fibrin (F, black arrows) and denuded calcific surface (gray arrow); 
         FIG. 23A  is an exemplary μOCT image of a large necrotic core (NC) fibroatheroma, demonstrating thick cholesterol crystals (CC), characterized by reflections from their top and bottom surfaces; 
         FIG. 23B  is an exemplary μOCT image of thin crystal (CC, gray arrow) piercing the cap of another necrotic core plaque (NC), shown in more detail in the inset; 
         FIG. 24A  is an exemplary μOCT image of various smooth muscle cells appearing as low backscattering spindle-shaped cells (inset); 
         FIG. 24B  is an exemplary μOCT image of smooth muscle cells producing collagen are spindle shaped, have a high backscattering interior (light gray arrow) and a “halo” of low backscattering (white arrow), which represents the cell body and collagen matrix, respectively (histology inset); 
         FIG. 25A  is an exemplary μOCT image of Taxus Liberte struts with/without polymer/drug, i.e., for polymer-coated struts, polymer reflection (PR), strut reflection (SR) and multiple reflections (MR 1 , MR 2 ) can be seen; 
         FIG. 25B  is an exemplary μOCT image of a cadaver coronary specimen with an implanted BMS shows struts devoid of polymer, covered by neointima; 
         FIG. 25C  is an exemplary μOCT image of a cadaver coronary specimen with implanted DES struts from another cadaver showing polymer overlying the strut reflections (P, inset); 
         FIG. 26A  is an exemplary μOCT image showing tissue (light gray arrow) has separated the polymer off of the stent strut and the polymer has fractured (white arrow); 
         FIG. 26B  is an exemplary μOCT image illustrating a superficial leukocyte cluster (red arrow) and adjacent attached leukocytes overlying the site of the polymer fracture; 
         FIG. 26C  is an exemplary μOCT image illustrating an inflammation at the edge of a strut (dashed region) from another patient; 
         FIG. 26D  is an exemplary μOCT image illustrating an uncovered strut, completely devoid of overlying endothelium (inset); 
         FIG. 27A  is a flow diagram of a process according to one exemplary embodiment of the present disclosure; and 
         FIG. 27B  is a flow diagram of the process according to another exemplary embodiment of the present disclosure. 
     
    
    
     Throughout the figures, the same reference numerals and characters, unless otherwise stated, are used to denote like features, elements, components or portions of the illustrated embodiments. Moreover, while the subject disclosure will now be described in detail with reference to the figures, it is done so in connection with the illustrative embodiments. It is intended that changes and modifications can be made to the described exemplary embodiments without departing from the true scope and spirit of the subject disclosure as defined by the appended claims. 
     DETAILED DESCRIPTION OF EXEMPLARY EMBODIMENTS 
     According to one exemplary embodiment of the present disclosure, two or more imaging channels can be utilized, e.g., at least one which providing the Bessel beam illumination or detection and at least another one of which providing a Gaussian beam illumination or detection. This exemplary configuration can facilitate three or more unique and separable illumination-detection combinations (e.g., Bessel-Bessel, Bessel-Gaussian, Gaussian-Gaussian, etc.), where each combination can correspond to a different OCT image. As shown in the exemplary graph of  FIG. 2 , coherent transfer functions (CTFs) for 2.5 μm diameter spots are provided. 
     For example,  FIG. 2  illustrates a graphical comparison of a diffraction limit  200 , extended focal range of 0.15 mm used in preliminary data  210 , and the exemplary results of an exemplary embodiment of a procedure or technique according to the present disclosure, hereinafter termed μOCT, with a focal range of 2.0 mm. According to one exemplary embodiment of the present disclosure the μOCT CTF can be generated, e.g., by combining Gaussian-Gaussian images  220 , Bessel-Gaussian images  230 , and Bessel-Bessel images  240 . 
     In another exemplary embodiment of the present disclosure, the exemplary μOCT CTF procedure/technique can be used and/or provided over an axial focus range that can be, e.g., more than 0.5 mm, 1 mm, 2 mm, etc. (as well as others). According to additional exemplary embodiments of the present disclosure, the transverse FWHM spot diameters can be less than 5 μm, 2 μm, 1 μm, etc. (as well as others). In still further exemplary embodiments of the present disclosure, the depth of focus can be extended a factor of, e.g., approximately 2, 5, 10, 20, 50, 100, etc. (and possibly more) compared to the illumination with a plane wave or Gaussian beam. In yet another exemplary embodiment of the present disclosure, the high, low, and medium spatial frequency content in the image can be at least partially restored by combining images with different transfer functions. 
       FIGS. 3A-3C  show exemplary OCT images of a cadaver coronary artery plaque obtained using an exemplary procedure/techniques according to exemplary embodiments of the present disclosure. For example, in  FIG. 3A  an exemplary Gauss-Gauss image contains low spatial frequency information. In  FIG. 3B , an exemplary Bessel-Bessel image provides high-resolution but loses low and mid spatial frequencies. Further, in  FIG. 3C , a combined μOCT image (e.g., Gauss−Gauss+Gauss−Bessel+Bessel−Bessel) is provided, and images are normalized and displayed with the same brightness/contrast values. 
       FIG. 4  shows a second exemplary embodiment of distal optics of a OCT catheter system according to the present disclosure. For example, the exemplary system of  FIG. 4  illustrates an axicon arrangement (e.g., pair) and a routing of the annulus (shown in a darker shade in  FIG. 4 ) and the Gaussian beam (shown in a darker shade in  FIG. 4 ) of the distal optics design according to this exemplary embodiment. In particular, the exemplary system illustrate din  FIG. 4  can generate a diffraction-limited CTF and an axial focus range (e.g., depth-of-focus) that can be more than, e.g., 10 times longer than the diffraction-limited depth-of-focus. The output of a waveguide  500  can be collimated by a collimator  510  located in a center of the exemplary catheter system. The collimated electro-magnetic radiation (e.g., light) can be transformed into an annular beam using two or more axicons  520 ,  530 . According to another exemplary embodiment, the axicons can be generated or produced using gradient index. 
     As shown in  FIG. 4 , a separate waveguide  540  can be routed through the center of the annulus. The output of the waveguide can be collimated by a collimator  550  located in the center of the annulus. Simulated transverse intensity profiles of the collimated annular and Gaussian beams are shown in an illustration of  FIG. 5A . Collimated annular and Gaussian beams can be focused onto the sample using one or more lens, such as a GRIN lens  560 . In addition to focusing two or more beams, the GRIN lens  560  can be configured to intentionally generate chromatic aberration, which can extend the axial focus further (as shown in an illustration of  FIG. 5B ), and to compensate the aberrations induced by the transparent outer sheath  570 . The electro-magnetic radiation (e.g., light) can be directed to the artery wall by a deflector  580 . 
       FIG. 6  shows a schematic diagram of an imaging system for generating μOCT images according to an exemplary embodiment of the present disclosure. As provided in the exemplary embodiment of  FIG. 6 , an output of a source  600  providing electro-magnetic radiation(s) (e.g., light radiation) can be linearly polarized by a linear polarizer  602 , and split into two or more beams by a beam splitter  604 . At least one of the beams can be redirected to an input port of a switch  606 . 
     At least one of outputs of the switch  606  can be transmitted through a beam splitter  610 , and coupled into a first light/electro-magnetic radiation guide  612 . Another other of the outputs of the switch  606  can be attenuated by an attenuator  614 , guided by a second light/electro-magnetic radiation guide  616  to a third beam splitter  618 , and redirected to a reference reflector  620  through an attenuator  622 , a third light/electro-magnetic radiation guide  624  and a dispersion compensation arrangement  626 . An output of the light guide  612  can be connected to Bessel illumination and Bessel detection channel of a catheter  628 . 
     As shown in  FIG. 6 , a further one of the outputs of the beam splitter  604  can be redirected to input port of a second three-port switch  630 . One of the outputs of the switch  630  can be transmitted through a beam splitter  632 , and coupled into a fourth light/electro-magnetic radiation guide  634 . Another one of the outputs of the switch  630  can be attenuated by an attenuator  635  guided by a fifth light guide  636  to a fourth beam splitter  638 , and redirected to a reference reflector  640  through an attenuator  642 , a fifth light guide  644  and a second dispersion compensation arrangement  646 . The output of the light guide  634  can be connected to a Gaussian illumination and Gaussian detection channel of the catheter  628 . 
     When the state of the switch  606  is 1, and the state of a fourth beam splitter  638  is 2, e.g., only the light/electro-magnetic radiation guide  612  can be illuminated so that the sample is illuminated by the Bessel illumination channel (see Table 1 of  FIG. 6 ). The back-scattered light from the sample can picked up by both, some or all of the Bessel and Gaussian detection channels of the catheter  628  (see Table 1 of  FIG. 6 ). The portion of electro-magnetic radiation/light picked up by the Bessel detection channel can be guided by the first electro-magnetic radiation/light guide  612  to the beam splitter  610 , where such radiation/light can be combined and interfered with the light from the reference reflector  620 . 
     Further, as illustrated in  FIG. 6 , at least part of the interference signal can be directed by the beam splitter  610  to a pinhole  648 . An output of the pinhole  648  can be collimated and split by a polarizing beam splitter  650 . One of outputs of the polarizing beam splitters  650  can be transmitted through a half wave plate  652 , and detected by a spectrometer  654 . Another of the outputs of the polarizing beam splitters  650  can be detected by a second spectrometer  656 . A portion of the electro-magnetic radiation/light picked up by the Gaussian detection channel can be guided by the light guide  634  to the beam splitter  632 , where it is combined and interfered with the light from the reference reflector  640 . At least part of the interference signal can be directed by the beam splitter  634  to a pinhole  658 . An output of the pinhole  658  can be collimated and split by a polarizing beam splitter  660 . At least one of outputs of the polarizing beam splitters  660  can be transmitted through a half wave plate  662 , and detected by a third spectrometer  664 . Another of the outputs of the polarizing beam splitters  660  can be detected by a fourth spectrometer  666 . 
     When the state of the switch  606  is 2 and the state of the switch  638  is 1, e.g., only the fourth electro-magnetic radiation/light guide  634  can be illuminated, so that the sample is illuminated by Gaussian illumination channel (shown in Table 1 of  FIG. 6 ). The back-scattered electro-magnetic radiation/light from the sample can be picked up by both Bessel and Gaussian detection channels of the catheter  630  (shown in Table 1 of  FIG. 6 ). At least one portion of the electro-magnetic radiation/light picked up by the Bessel detection channel is guided by the electro-magnetic radiation/light guide  612  to the beam splitter  610 , where it can be combined and interfered with the light from the reference reflector  620 . At least part of the interference signal can be directed by the beam splitter  610  to a pinhole  648 . An output of the pinhole  648  can be collimated and split by a polarizing beam splitter  650 . At least one of outputs of the polarizing beam splitters  650  can be transmitted through a half wave plate  652 , and detected by a spectrometer  654 . Another of the outputs of the polarizing beam splitters  650  can be detected by a second spectrometer  656 . 
     The portion of light picked up by the Gaussian detection channel is guided by the electro-magnetic radiation/light guide  634  to the beam splitter  632 , where it is combined and interfere with the light/radiation from the reference reflector  640 . At least part of the interference signal can be directed by the fourth electro-magnetic radiation/light guide  634  to a pinhole  658 . The output of pinhole  658  is collimated and split by a polarizing beam splitter  660 . At least one of the two outputs of the polarizing beam splitters  660  can be transmitted through a half wave plate  662 , and detected by a third spectrometer  664 . Another of the outputs of the polarizing beam splitters  660  can be detected by a fourth spectrometer  666 . 
     Such exemplary polarization-diverse detection scheme/configuration shown in  FIG. 6  implemented by the combination of the polarizing beam splitter  650 , the half wave plate  652  and the spectrometers  654 ,  656 , and/or a combination of the polarizing beam splitter  660 , the half wave plate  662  and the spectrometers  664 ,  666  can reduce and/or eliminate artifacts associated with tissue or optical fiber birefringence. The exemplary embodiment of the μOCT catheter system according the present disclosure illustrated in  FIG. 6  can contain multiple waveguides that can, e.g., independently transmit and/or receive light/radiation from the catheter to waveguides  612  and  632 . The detected signal can be digitized and transferred by a computer  668  via an image acquisition board  670 . Data can be digitally displayed on or via a monitor  672 , and/or stored in a storage device  674 . 
     According the present disclosure, the μOCT detection technology can be implemented using, in one exemplary embodiment, a time domain OCT (TD-OCT) system, in another exemplary embodiment, a spectral-domain (SD-OCT) system, and, in yet another exemplary embodiment, an optical frequency domain interferometry (OFDI) system. Complex images and/or real images from the different transfer function illumination and detection configurations can be acquired using the exemplary embodiment of the imaging system according to the present disclosure. In one exemplary embodiment, such exemplary images can be filtered and recombined to generate a new image with an improved quality and a CTF that more closely approximates the diffraction limited CTF. The exemplary images with different transfer functions can be filtered or recombined incoherently and/or coherently to generate a new image with a CTF procedure/technique that more closely approximates the diffraction limited CTF procedure/technique. 
       FIG. 7  shows another exemplary embodiment of distal optics configuration of a OCT catheter according to the present disclosure for generating a diffraction-limited CTF and an axial focus range (e.g., depth-of-focus) that can be more than, e.g., approximately 10 times longer than the diffraction-limited depth-of-focus. 
     For example, an output of a waveguide  700  can be collimated by a collimator  710 . Indeed, the waveguide  700  can be routed through the annular beam and is collimated Gaussian beam will be routed through the center of the annulus. The collimated light can be transformed into an annular beam through two or more axicons, such as, e.g., GRIN axicons  720 ,  730 . A separate waveguide  740  can be routed through a center of the annulus. An output of the waveguide  740  can be collimated by a collimator  750  located in the center of the annulus. The collimated annular and Gaussian beams can be focused onto the sample using one or more lens(es)  760 , which can be, e.g., one or more GRIN lenses. In addition to focusing the beams, the GRIN lens  760  can be configured and/or structured to intentionally generate chromatic aberration(s), which can extend the axial focus further and compensate for the aberrations induced by a transparent outer sheath. The light/radiation can be directed to the artery wall by a deflector  770 . 
       FIG. 8  shows another exemplary embodiment of the distal optics configuration of the OCT catheter according to the present disclosure. Such exemplary configuration can be used to generate a diffraction-limited CTF and depth of focus that is, e.g., more than 10 times longer than the diffraction-limited depth-of-focus. An output of a waveguide  800  can be collimated by a collimator  810 . A pupil aperture created by the collimator  810  can be split into two or more beams, i.e., central circular beam(s) and an annular beam. One or more lenses  820 , such as an objective lens, achromat lens, aplanat lens, or GRIN lens, that has an aperture substantially the similar as or identical to a central zone can focus a low NA Gaussian beam into the tissue or the sample. 
     The annular beam can be transmitted through a spacer  830 , and focused into the sample by an annular axicon lens  840  with an aperture that is substantially similar or identical to the annular beam. The beams can be directed to the sample by a deflector  850 . There can be four images generated from four channels, e.g., central illumination/central detection, central illumination/annular detection, annular illumination/annular detection, annular illumination/central detection. The optical pathlength of the lens  820  can be configured to be different from that of the spacer  830  so that each of, e.g., four images generated can be pathlength encoded. In this exemplary embodiment, the different images can be detected, and their CTF can be combined as per the exemplary methods and/or procedures described herein. 
       FIG. 9  shows another exemplary embodiment of the distal optics configuration of the OCT catheter system according to the present disclosure, which can be used for generating a diffraction-limited CTF and a depth of focus that is longer than the diffraction-limited depth-of-focus. For example, as illustrated in  FIG. 9 , the output of a waveguide  900  can be collimated by a collimator  910 . A pupil aperture created by the collimator  910  can be split into two or more zones by a circular glass window  920  positioned at the center of the objective lens aperture, e.g., (i) a central circular zone that is transmitted through the circular glass window  920 , and (ii) an annular zone. The central circular beam can be focused as a low NA Gaussian beam into the tissue and/or sample, and the annular beam can be focused into a Bessel beam focus in the tissue by the lens  930 . A glass window can have a higher refractive index than air, and the thickness of the window can be so chosen such that the light/radiation field that undergoes different channel can be path-length separated and/or encoded. In each A line, there can be three or more segments of signal coming from the (e.g., 4) channels: central illumination/central detection, central illumination/annular detection, annular illumination/annular detection, annular illumination/central detection. 
       FIG. 10  shows a further exemplary embodiment of the distal optics configuration of the OCT catheter system for generating a diffraction-limited CTF and a depth of focus that can be longer than the diffraction-limited depth-of-focus. An output of a waveguide  1000  can be collimated by a collimator  1010 . A pupil aperture created by the collimator  1010  can be split into a number of concentric zones  1020 ,  1030 ,  1040 . A multifocal lens, such as, e.g., a GRIN lens, can be used so that the beam in each zone can be focused to a different axial focal position. The scattered light/radiation from each zone can be optical pathlength-encoded so that such scattered beams do not interfere with each other. In this exemplary embodiment, the different images can be detected, and their CTF combined pursuant to the exemplary methods and procedures described herein. 
       FIG. 11  shows yet another exemplary embodiment of the distal optics configuration of the OCT catheter system for generating a diffraction-limited CTF and an axial focus range (e.g., depth-of-focus) that is longer than the diffraction-limited depth-of-focus. For example, an output of a point object  1100  can be transformed by a mirror tunnel device  1110  to multiple orders of light/radiation beams, e.g., zeroth order beam  1120 , −1st order beam  1130 , and −2nd order beam  1140 , etc. When a focusing device  1150  is employed so that most or all the order of rays are focused at the same focal position in the sample, each order of rays can contain a unique band of spatial frequency of the illumination/detection CTF of the focusing device. These orders can, in yet another exemplary embodiment, be path length-encoded so that images generated therein can be detected, and their CTF combined using the different images corresponding to the different orders as per the exemplary CTF combination methods and/or procedures described herein. 
       FIG. 12  shows another exemplary embodiment of the distal optics configuration of the OCT catheter system according to the present disclosure for generating a diffraction-limited CTF and a depth of focus that is longer than the diffraction-limited depth-of-focus. As illustrated in  FIG. 12 , an output of a waveguide  1200  can be focused by a half ball lens  1210 . A planar surface of the half ball lens  1210  can have a binary phase pattern  1220 . In one further exemplary embodiment, the depth of the pattern can be configured to produce a small phase shift, e.g., such as a pattern depth of 198 nm ( 7   c  phase shift at 850 nm). In another exemplary embodiment, the top surface can be coated with a reflecting coating, such as Au, and a bottom surface can be coated with the same and/or another coating such as Al, with the final phase shift being given by a curve  1300  shown in a graph of  FIG. 13 , which illustrates an optical phase length difference of the glass mask (e.g., no metal coating) and a total phase shift (e.g., mask+coating). 
     A curve  1310  and a curve  1320  of the graph of  FIG. 13  can have a wavelength-dependent phase change of the p-polarized light upon reflection at BK7-Al and BK7-Au, respectively, with an incident angle of 45 degrees. The curve  1330  can be the wavelength dependent phase shift of the light caused by, e.g., 198 nm height difference upon 45 degree reflection at BK7-air interface. A binary phase mask can be optimized to produce an extended axial focus (as shown in an illustration of  FIG. 14   b ) compared with the diffraction limited axial focus (as shown in an illustration of  FIG. 14   a ). The light/radiation transmitted from the surfaces with different phase shifts can generate different transfer functions, which can be detected and combined to create a new image with a different CTF pursuant to the exemplary methods and/or procedures described herein. 
       FIG. 15A  shows a side-cut-away view of a diagram of another exemplary embodiment of the distal optics configuration of the OCT catheter system for generating a diffraction-limited CTF and an depth of focus longer than the diffraction-limited depth-of-focus. For example, the system of  FIG. 15A  generates the results by a factor of, e.g., approximately 2, 5, 10, 20, 10, 100, etc. An output of a waveguide  1500  can be collimated by one or more lens(es)  1510 . The collimated beam can be spatially modulated by a phase doublet  1520 , which can include a positive phase plate and a negative phase plate with the same or similar phase pattern. By matching Abbe number of the positive phase plate and the negative phase plate, the wavelength dependent phase error can be canceled or reduced.  FIG. 15B  shows an exemplary graph of transverse phase profiles of an exemplary mask (e.g., BK7-SNPH2 phase doublet mask) illustrated in  FIG. 15A  For example, by choosing Ohara S-NPH2 (Vd=18.896912, Nd=1.922860) and Schott BK7 (Vd=64.167336, Nd=1.5168), with depth 7.2554 um and 13.4668 um respectively, the phase profile is shown in  FIG. 15B . The spatially modulated beam can be focused into an extended axial focus by an objective lens  1530 . 
       FIG. 16  shows still another exemplary embodiment of the distal optics configuration of the OCT catheter system for generating a diffraction-limited CTF and depth of focus according to the present disclosure that is longer than the diffraction-limited depth-of-focus, by a factor of preferably approximately 2, 5, 10, 20, 10, 100, etc. An output of a light source  1600  can be split by a beam splitter  1610 . The beam aperture of at least one of the outputs of the beam splitter can be split or separated by a rod mirror  1620  into two or more regions. For example, the rod mirror  1620  can redirect the central part of the beam to a reference reflector  1630  through an objective lens  1640 . The annular beam can be focused into the sample by a second objective lens  1660  that can be substantially similar or identical to one or more lens(es)  1640  into a Bessel focus featured with extended axial focus and super-resolution in transverse direction (as shown in the exemplary μOCT images of  FIG. 18D ). The light back-scattered from the sample is combined with the light reflected from the reference reflector through the rod mirror at a pinhole  1660 . The output of the pinhole  1660  is detected by a spectrometer  1670 . The objective lens  1650  is configured to intentionally generate chromatic aberration and spherical aberration, which extend the axial focus further (as shown in the exemplary μOCT images of  FIGS. 18C and 18D ).  FIG. 18A  shows an exemplary μOCT image of a coronary plaque showing multiple leukocytes (arrows). In addition,  FIG. 18B  shows an exemplary μOCT image of a coronary plaque illustrating multiple leukocytes (arrows) of two different cell types, one smaller cell with scant cytoplasm, consistent with a lymphocyte (L) and another, larger cell with a highly scattering cytoplasm, indicative of a monocyte (M). 
     Indeed,  FIG. 18A  illustrates an exemplary μOCT image of a coronary plaque showing multiple leukocytes  1800  which has been generated using the exemplary embodiment(s) of the methods, systems and apparatus according to the present disclosure.  FIG. 18B  illustrates an exemplary μOCT image of a coronary plaque showing multiple leukocytes of two different cell types, one smaller cell  1810  with scant cytoplasm, consistent with a lymphocyte and another, larger cell  1820  with a highly scattering cytoplasm, suggestive of a monocyte.  FIG. 18C  illustrates an exemplary μOCT image of a coronary plaque showing a cell  1830  with an indented, bean-shaped nucleus characteristic of a monocyte.  FIG. 18D  illustrates an exemplary μOCT image of a coronary plaque showing a leukocyte  1840  with a multi-lobed nucleus, suggestive of a neutrophil attached to the endothelial surface.  FIG. 18E  illustrates an exemplary μOCT image of a coronary plaque showing multiple leukocytes  1850 , tethered to the endothelial surface by pseudopodia  1860 .  FIG. 18F  illustrates an exemplary μOCT image of a coronary plaque showing cells  1870  with the morphology of monocytes in this cross-section and inset transmigrating through the endothelium  1880 . Further,  FIG. 18G  illustrates an exemplary μOCT image of multiple leukocytes  1890  distributed on the endothelial surface. 
       FIG. 19A-19E  show exemplary images which have been generated using the exemplary embodiment(s) of the methods, systems and apparatus according to the present disclosure. For example  FIG. 19A  illustrates an exemplary μOCT image of platelets  1900  (P) adjacent to a leukocyte characteristic of a neutrophil  1910  (N), which is also attached to a small platelet  1920  (yellow arrow).  FIG. 19B  illustrates an exemplary μOCT image of fibrin  1930  (F) which is visible as linear strands bridging a gap in the coronary artery wall.  FIG. 19C  illustrates an exemplary μOCT image of a cluster of leukocytes  1940  (L), adherent to the fibrin in an adjacent site to  FIG. 19B .  FIG. 19D  illustrates an exemplary μOCT image of Fibrin thrombus  1950  (T) with multiple, entrapped leukocytes.  FIG. 19E  an μOCT image of a more advanced thrombus  1960  (T) showing a leukocyte  1970  (arrow) and fibrin strands  1980  (inset, see  FIG. 19F ). 
       FIGS. 20A-20D  show further exemplary images which have been generated using the exemplary embodiment(s) of the methods, systems and apparatus according to the present disclosure. For example,  FIG. 20A  illustrates a cross-sectional exemplary μOCT image of endothelial cells  2000  in culture.  FIG. 20B  shows an en face exemplary μOCT image of endothelial cells  2010  in culture.  FIG. 20C  illustrates an exemplary μOCT image of native swine coronary artery cross-section  2020 .  FIG. 20D  shows a three-dimensional rendering of the swine coronary artery, demonstrating endothelial “pavementing”  2030 .\ 
       FIGS. 20A-20D  show further exemplary images which have been generated using the exemplary embodiment(s) of the methods, systems and apparatus according to the present disclosure.  FIG. 21A  shows an exemplary μOCT image of microcalcifications which are seen as bright densities within the μOCT image of the fibrous cap  2100 .  FIG. 21B  illustrates an exemplary μOCT image of microcalcifications which are seen as purple densities on the corresponding histology  2110 . 
     Further,  FIGS. 20A-20D  illustrate further exemplary images which have been generated using the exemplary embodiment(s) of the methods, systems and apparatus according to the present disclosure. For example,  FIG. 22A  shows an exemplary μOCT image of a large calcium nodule, demonstrating disrupted intima/endothelium  2200 .  FIG. 22B  shows an expanded view of an exemplary region enclosed by the red box shows microscopic tissue strands, consistent with fibrin  2210 , adjoining the unprotected calcium  2220  to the opposing detached intima.  FIG. 22C  shows a corresponding histology illustrating fibrin  2230  and denuded calcific surface  2240 . 
     In addition,  FIGS. 23A-26C  illustrate further exemplary images which have been generated using the exemplary embodiment(s) of the methods, systems and apparatus according to the present disclosure. For example,  FIG. 23A  shows an exemplary μOCT image of a large necrotic core  2300  fibroatheroma, demonstrating thick cholesterol crystals  2310 , characterized by reflections from their top and bottom surfaces.  FIG. 23B  shows an exemplary μOCT image of thin crystal  2320 , piercing the cap of another necrotic core plaque  2330 , shown in more detail in the inset.  FIG. 24A  shows an exemplary μOCT image of many smooth muscle cells  2400  appear as low backscattering spindle-shaped cells (inset).  FIG. 24B  shows an exemplary μOCT image of smooth muscle cells producing collagen are spindle shaped, have a high backscattering interior  2410  and a “halo” of low backscattering  2420 , which can represent the cell body  2430  and collagen matrix  2440 , respectively (e.g., histology inset). 
       FIG. 25A  shows an exemplary μOCT image of Taxus Liberte (Boston Scientific, Natick, Mass.) struts without polymer  2500 , with polymer without drug  2510 , and with polymer with drug  2520 . For polymer-coated struts, polymer reflection  2530 , strut reflection  2540  and multiple reflections  2550  and  2560  can be seen.  FIG. 25B  shows an exemplary μOCT image of a cadaver coronary specimen with an implanted BMS  2570  shows struts devoid of polymer, covered by neointima  2580 .  FIG. 25C  shows an exemplary μOCT image of a cadaver coronary specimen with implanted DES struts  2590  from another cadaver showing polymer overlying the strut reflections  2595  (inset). 
     In addition,  FIG. 26A  shows an exemplary μOCT image showing tissue  2600  has separated the polymer  2610  off of the stent strut  2620  and the polymer has fractured  2630 .  FIG. 26B  shows an exemplary μOCT image showing superficial leukocyte cluster  2640  and adjacent attached leukocytes  2650  overlying the site of the polymer fracture  2660 .  FIG. 26C  shows an exemplary μOCT image showing inflammation  2670  at the edge of a strut  2680  from another patient.  FIG. 26D  shows an exemplary μOCT image showing uncovered strut  2690 , completely devoid of overlying endothelium. 
       FIG. 27A  shows a flow diagram of a method for providing data associated with at least one portion of at least one sample according to one exemplary embodiment of the present disclosure. For example, in procedure  2710 , at least one first radiation is forwarded to at least one portion of the sample through at least one optical arrangement (e.g., as described in various exemplary embodiments herein), and at least one second radiation is received from the portion which is based on the first radiation. Based on an interaction between the optical arrangement and the first radiation and/or the second radiation, the optical arrangement has a first transfer function. Then, in procedure  2720 , at least one third radiation is forwarded to the portion through such optical arrangement, and at least one fourth radiation is received from the portion which is based on the third radiation. Based on an interaction between this optical arrangement and the third radiation and/or the fourth radiation, the optical arrangement has a second transfer function. The first transfer function can be at least partially different from the second transfer function. Further, in procedure  2730 , the data associated with the portion(s) can be generated based on the second and fourth radiations. 
       FIG. 27B  shows a flow diagram of the method for providing data associated with at least one portion of at least one sample according to another exemplary embodiment of the present disclosure. For example, in procedure  2760 , at least one first radiation is forwarded to at least one portion of the sample through at least one first optical arrangement (e.g., as described in various exemplary embodiments herein), and at least one second radiation is received from the portion which is based on the first radiation. Based on an interaction between the first optical arrangement and the first radiation and/or the second radiation, the first optical arrangement has a first transfer function. Then, in procedure  2770 , at least one third radiation is forwarded to the portion through at least one second optical arrangement, and at least one fourth radiation is received from the portion which is based on the third radiation. Based on an interaction between the second optical arrangement and the third radiation and/or the fourth radiation, the optical arrangement has a second transfer function. The first transfer function can be at least partially different from the second transfer function. Further, in procedure  2780 , the data associated with the portion(s) can be generated based on the second and fourth radiations. 
     The foregoing merely illustrates the principles of the present disclosure. Various modifications and alterations to the described embodiments will be apparent to those skilled in the art in view of the teachings herein. For example, more than one of the described exemplary arrangements, radiations and/or systems can be implemented to implement the exemplary embodiments of the present disclosure Indeed, the arrangements, systems and methods according to the exemplary embodiments of the present invention can be used with and/or implement 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 (which published as International Patent Publication No. WO 2005/047813 on May 26, 2005), U.S. patent application Ser. No. 11/266,779 filed Nov. 2, 2005 (which published as U.S. Patent Publication No. 2006/0093276 on May 4, 2006), U.S. patent application Ser. No. 10/861,179 filed Jun. 4, 2004, U.S. patent application Ser. No. 10/501,276 filed Jul. 9, 2004 (which published as U.S. Patent Publication No. 2005/0018201 on Jan. 27, 2005), U.S. patent application Ser. No. 11/445,990 filed Jun. 1, 2006, International Patent Application PCT/US2007/066017 filed Apr. 5, 2007, and U.S. patent application Ser. No. 11/502,330 filed Aug. 9, 2006, 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 present disclosure and are thus within the spirit and scope of the present disclosure. 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.