MX2007015288A - Oct using spectrally resolved bandwidth - Google Patents

Abstract

The present invention is related to a system for optical coherence tomographic imaging of turbid (i.e., scattering) materials utilizing multiple channels of information. The multiple channels of information may be comprised and encompass spatial, angle, spectral and polarization domains. More specifically, the present invention is related to methods and apparatus for utilizing optical sources, systems or receivers capable of providing (source), processing (system) or recording (receiver) a multiplicity of channels of spectral information for optical coherence tomographic imaging of turbid materials. In these methods and apparatus the multiplicity of channels of spectral information that can be provided by the source, processed by the system, or recorded by the receiver are used to convey simultaneously spatial, spectral or polarimetric information relating to the turbid material being imaged tomographically. The multichannel optical coherence tomographic methods can be incorporated into an endoscopic probe for imaging a patient. The endoscope comprises an optical fiber array and can comprise a plurality of optical fibers adapted to be disposed in the patient. The optical fiber array transmits the light from the light source into the patient, and transmits the light reflected by the patient out of the patient. The plurality of optical fibers inthe array are in optical communication with the light source. The multichannel optical coherence tomography system comprises a detector for receiving the light from the array and analyzing the light. The methods and apparatus may be applied for imaging a vessel, biliary, GU and/or GI tract of a patient.

Description

OPTICAL COHERENCE TOMOGRAPHY USING MICHO DS? BM? D ESP? CTRALLY REDUCED FIELD OF THE INVENTION The present invention relates to a system for tomographic photoreception of optical coherence of turbid (ie, diffuse) materials using multiple information channels . The multiple information channels may be encompassed and encompass spatial, angle, spectral, and polarization domains. More specifically, the present invention relates to methods and apparatus that use optical sources, systems or receivers capable of providing (source), processing (system) or recording (receiver) a multiplicity of spectral information channels for tomographic photoreception of optical coherence of turbid materials. In these methods and apparatuses the multiplicity of spectral information channels that can be provided by the source, processed by the system, or recorded by the receiver is used to transport simultaneously the spatial, spectral or polarimetric information in relation to the turbid material that is being photorecepting topographically. The multichannel optical coherence tomographic methods can be incorporated into an endoscopic probe for photoreception of a patient. The endoscope comprises a fiber optic array and may comprise a plurality of Ref. 187497 optical fibers adapted to be disposed in the patient. The arrangement of optical fibers transmits light from the light source within the patient, and transmits the light reflected by the patient outside the patient. The plurality of optical fibers in the array is in optical communication with the light source. The multichannel optical coherence tomography system comprises a detector to receive light from the array and analyze the light. The methods and apparatuses can be applied for the photoreception of a container, biliary tract, GU and / or Gl of a patient. BACKGROUND OF THE INVENTION Myocardial infarction or heart attack are still the leading cause of death in our society. Unfortunately, most of us can identify a family member or a close friend who has suffered a myocardial infarction. Until recently many researchers believe that coronary arteries critically blocked with atherosclerotic plaque that subsequently progresses to total occlusion was the main mechanism for myocardial infarction. Recent evidence from many research studies, however, clearly indicates that most heart attacks are due to the sudden rupture of coronary arteries not critically narrowed due to the sudden rupture of the plaque. For example, Little et al (Little, WC, Do nes, TR, Applegate, RJ, The underlying coronary anguigraphy, Clin Cardiol 1991; 14: 868-874, incorporated by reference herein) observed that approximately 70% of the Patients suffering from a ruptured acute plaque were started on plaques that were less than 50% occluded as revealed by previous coronary angiography. This and similar observations have been confirmed by other investigators (Nissen, S. Coronary angiography and intravascular ultrasound, Am J Cardiol 2001; (suppl): 15A-20A, incorporated herein by reference). The development of technologies to identify these unstable plaques controls the potential to substantially decrease the incidence of acute coronary syndromes that usually lead to premature death. Unfortunately, there is no method currently available to the cardiologist that can be applied to specify which coronary plaques are vulnerable and thus prone to rupture. Although the treadmill test has been used for decades to identify patients with a higher cardiovascular risk, this method does not have the specificity to differentiate between stable and vulnerable plaques that are prone to rupture and often result in myocardial infarction. Considering that there is a large amount of information regarding the pathology of unstable plate technologies (determined at autopsy) based on the identification of the well-described pathological appearance of the vulnerable plaque offers a promising long-term strategy to solve this problem . The unstable plaque was first identified and characterized through pathologists in the early 80s. Davis and his colleagues observed that with the reconstruction of serial histological sections in patients with acute myocardial infarctions associated with death, a rupture or fissure of the atheromatous plaque was evident (Davis MJ, Thomas AC Plaque fissuring: "the cause of acute myocardial infaretion, sudde death, and crescendo angina." Br Heart J 1985; 53: 363-373, incorporated herein by reference). The ulcerated plaques are further characterized as having a thin fibrous layer, increased macrophages with decreased smooth muscle cells and an increased lipid center when compared to non-ulcerated atherosclerotic plaques in human aortas (Davis MJ, Richardson OD, N olf, Katz DR, Mann J. Risk of thrombosis in human atherosclerotic plaques: role of extracellular lipid, macrophage, and smooth muscle cell content, incorporated by reference herein). In addition, no correlation was observed in the size of the lipid group and the percentage of stenosis when the photoreception was made through coronary angiography. In fact, most cardiologists agree on the advancement of unstable plaques to more stable stenotic plaques through advancement by rupturing the formation of a mural thrombus and the remodeling of the plaque, but without luminal occlusion complete (Topo EJ, Rabbaic R. Strategies to achieve coronary arterial plaque stabilization, Cardiovasc Res 1999; 41: 402-417, incorporated herein by reference). Neovascularization with intraplaque hemorrhage may also play a role in the progression of small lesions (less than 50% occluded) to significantly larger plaques. Still, if the only feature of the unstable plaque could be recognized through the cardiologist and then stabilized, a dramatic decrease could be made in both acute myocardial infarction and unstable angina syndromes, and in the sudden advance of artery disease. coronary The present invention uses deep resolved light reflection or Optical Coherence Tomography (OCT, for its acronym in English) to identify the pathological features that have been identified in the vulnerable plaque. In OCT, light from a broadband light source or tunable laser source is captured in the interferometer with a portion of light directed towards the container wall and the proportion directed to the reference surface. The distal end of the optical fiber is interconnected with a catheter for interrogation of the coronary artery during a cardiac catheterization procedure. The light reflected from the plate recombines with the signal from the reference surface forming the interference fringes (measured through a photovoltaic detector) allowing photoreception resolved in depth of the plate on a scale of microns. OCT uses a tunable narrow-line-width laser source or a super-luminescent diode source that emits light over a wide bandwidth (wavelength distribution) to perform topographic images in situ with axial resolution of 10-20 μm and tissue penetration of 2-3 mm. OCT has the potential to photorecept tissues at the level of a single cell. In fact, the inventors have recently used optical sources with a wider band width as second femto pulsed lasers, such that the axial resolution is improved to 4 microns or less. With this resolution, the OCT can be applied to visualize intimate covers, their thickness, and details of the structure including fissures, the size and extension of the group of underlying lipids and the presence of inflammatory cells. In addition, near-infrared light sources used in OCT instrumentation can penetrate into the highly calcified tissue regions characteristic of advanced coronary artery disease. With cellular resolution, the application of OCT can be used to identify other details of the vulnerable plaque such as the infiltration of monocytes and macrophages. In sum, the application of OCT can provide detailed images of a pathological specimen without cutting or disturbing the tissue. A concern with the application of this technology to photorecept atherosclerotic plaques inside the arterial lumen is the strong dispersion of light due to the presence of red blood cells. Once the catheter system is placed in the coronary artery, blood flow between the OCT fiber optic and the artery can obscure the penetration of light into the vessel wall. A proposed solution is the use of salt discharges. The use of saline is limited, however, since myocardial ischemia eventually occurs in the distal myocardium. The inventors have proposed the use of artificial hemoglobin instead of saline. Artificial hemoglobin is not in particles and therefore does not diffuse light. In addition, artificial hemoglobin is about to be approved by the United States Food and Drug Administration as a substitute for blood and may carry oxygen needed to prevent myocardial ischemia. Recently, the inventors demonstrated the availability of using artificial hemoglobin to reduce the diffusion of light by means of blood in the coronary arteries of the mouse myocardium (Villard JW, Feldman MD, Ki Jeehyun, Milner TE, Free an GL. a blood substitute for determining right ventricular thinning of instant murine with optical coherence tomography, Circulation 2002; Volume 105: pp. 1843-1849, incorporated herein by reference). The first prototype of an OCT catheter for photoreceptor coronary plaques has been constructed and is currently being tested by researchers at Harvard Boston - MIT (Jang IK, BE Mist, DH Kang, and others.) Visualization of coronary atherosclerotic plaques in patients using optical coherence tomography: comparison with intravascular ultrasound JACC 2002; 39: 604-609, incorporated herein by reference) in association with Light Lab Co. The prototype catheter consists of a single light source and is capable of photoreceiving on an arc of 360 degrees of a coronary arterial lumen through the rotation of an axis that rotates the optical fiber. Because the rotating shaft is housed outside the body, the rotating bar in the catheter must rotate with a uniform angular velocity in such a way that the light can be focused in equal intervals of time in each angular segment of the coronary artery. Mechanical entrainment in the axis of rotation can produce significant distortion and objects in OCT images recorded in the coronary artery. Unfortunately, because the catheter will always be forced to make several frictions between the entry point and the femoral artery into the coronary artery (for example, a 180-degree turn around the aortic arch), uneven mechanical entrainment will result. OCT image objects. When the application of OCT is exchanged from total anatomical structures of photoreception of the coronary artery to its capacity of photoreception at the level of a single cell, the non-uniform rotation of the prototype OCT of individual fiber will become a problematic source in increase of distortion and image object. Essentially, current endoscope-type single-channel OCT systems developed by Light Lab Co. suffer from a non-constant rotation speed that forms irregular images of a target vessel. See the patent of E. U. A. No. 6,134,003, incorporated herein by reference. His method of a rotating shaft to spin a fiber in individual mode is prone to produce an artifact. The catheter will always be forced to make several bends from its entrance into the femoral artery, around 180 degrees around the aortic arch, towards its final destination in the coronary artery. All these bends will cause non-uniform friction on the rotating shaft, and an uneven time distribution of light on the 36-degree arc of the coronary artery. Since the application of OCT is exchanged from total anatomical structures in the coronary artery to its ability to photorecept the level of a single cell, the non-uniform rotation of the single fiber OCT will become a major source of larger artifacts. The present invention solves the rotational distortion and related artifact problems through the development of an OCT multiphase array catheter. With the incorporation of 10-60 individual OCT fibers within a single catheter, the rotation of the fiber optic or similar element (eg, a mirror driven with a micromotor) and the associated image distortion and artifacts are eliminated and the resolution spatial can be improved. The catheter will allow 10-60 individual sources of light to independently photorecept the 360-degree arc of the coronary artery lumen. An additional advantage of the multiphase array is the provision of a higher spatial resolution of the object being interrogated compared to the individual fiber designs. Many researchers recognize that an individual rotating fiber or micromotor driven mirrors used in current designs will not allow photoreception at the level of a single cell while the multiphase array method can provide cell resolution. The construction of an OCT multiphase array catheter requires the resolution of a number of problems using innovative design solutions. The successful design and demonstration of the catheter requires the development of an optical channel containing 10-60 individual fibers in a diameter of 1.5 m. Each fiber requires a lens to focus light, and a mirror manufactured using nanotechnology to redirect light from each fiber at 90 degrees from the catheter to the luminal surface of the coronary artery. In addition, each of the 10-60 light paths has to be divided again for both reference and artery trajectories. The present invention provides the design solutions for both the catheter interferometer and the multichannel interferometer. BRIEF DESCRIPTION OF THE INVENCIES The present invention pertains to an endoscope for a patient. The endoscope comprises light producing means, such as a light source. The endoscope comprises an array of optical fiber comprising a plurality of optical fibers adapted to be disposed in the patient. The fiber optic array transmits light from the light producing means to the patient, and transmits the light reflected by the patient outside the patient. The plurality of optical fibers of the arrangement in optical communication with the light producing means. The endoscope comprises a detector to receive light from the array and analyze the light. The plurality of optical fibers of the array in optical communication with the detector. The present invention pertains to a method for photoreception of a patient. The method comprises the steps of transmitting light from a light source within an array of optical fiber comprising a plurality of optical fibers in the patient. There is the step of transmitting the light reflected by the patient outside the patient. There is the step of receiving the light from the array to a detector. There is the step of analyzing the light with the detector. The present invention pertains to an apparatus for studying an object. The apparatus comprises means for producing light. The apparatus comprises means for analyzing the light that is reflected from the object based on polarization, space, position or angle. The present invention pertains to an apparatus for studying an object. The apparatus bought means to produce light. The apparatus comprises means for analyzing the light that is reflected from the object based on polarization. The present invention pertains to an apparatus for studying an object. The apparatus comprises means for producing light. The apparatus comprises means for analyzing the light that has been reflected from the object based on space. The present invention pertains to an apparatus for studying an object. The apparatus comprises means for producing light. The apparatus comprises means for analyzing the light that has been reflected from the object based on the angle. The present invention pertains to a method for studying an object. The method comprises the steps of producing light. The method comprises the steps of analyzing the light that has been reflected from the object based on polarization, space, position or angle. The present invention pertains to a method for studying an object. The method comprises the steps of producing light. The method comprises the steps of analyzing the light that has been reflected from the object based on polarization. The present invention pertains to a method for studying an object. The method comprises the steps of producing light. The method comprises the steps of analyzing the light that has been reflected from the object based on space. The present invention pertains to a method for studying an object. The method comprises the steps of producing light. The method comprises the steps of analyzing the light that has been reflected from the object based on the angle. BRIEF DESCRIPTION OF THE FIGURES In the appended figures, the preferred embodiment of the invention and the preferred methods of practicing the invention are illustrated, wherein: Figure 1 is a schematic representation of an overall view of the present invention. Figure 2 is a top view of an input arm (light source) of the present invention. Figure 3 is a schematic representation of a side view of the input arm (light source). Figure 4 is a schematic representation of a fiber-based solution for the input arm. Figure 5 is a schematic representation of a side view of a sample arm. Figure 6 is a schematic representation of an axial view of the sample arm. Figure 7 is a schematic representation of a top view of the axicon lenses. Figure 8 is a schematic representation of a fiber optic array of the sample arm. Figures 9A and 9B are a schematic representation of a perspective view of a probe tip of the sample arm which emphasizes the mirrors to refocus the light of the tissue of interest. Figure 10 is a schematic representation of a side view of a tip groove with a fiber attached at the end to a 45a angled mirror (reflection). Figure 11 is a schematic representation of a top view of the tip with a bonded fiber. Figure 12 is a schematic representation of a first step for the manufacture of each fiber lens of the sample arm. Figure 13 is a schematic representation of a second step in the manufacture of each fiber lens of the sample arm. Figure 14 is a schematic representation of a reference arm of the present invention. Figure 15 is a schematic representation of a top view of the detection arm of the present invention. Figure 16 is a schematic representation of a side view of the detection arm. Figures 17 and 17A are an alternative schematic representation of the probe probe of the sample arm. Figures 18A and 18B are schematic representations of a hydraulic mechanism. Figures 19A and 19B are schematic representations of illustrative views of the hydraulic mechanism. Figures 20A-20D are schematic representations of different views of a threaded shaft of the hydraulic mechanism. Figures 21A and 21B are schematic representations of the fiber-axis support. Figures 22A-22C are schematic representations of the fiber slots. Figure 23 is a side view of the micro-mirror.

Figure 24 is a perspective view of the micro-mirror. Figure 25 is a perspective view of the micro-mirrors with a portion irradiated through a laser beam. Figure 26 is a perspective view of the micro-mirror having a deformation generated by being irradiated through a laser beam as shown in Figure 25. Figure 27 is a schematic representation of the micro-mirror being continuously heated by a laser beam that shines in different places of the micro-mirror. Figure 28 is a schematic representation of the change resulting from the tilting direction of the micro-mirror due to the change of location of the laser beam the icro-mirror. Figure 29 is a schematic representation of the micro-mirror on the probe cover relative to the fibers. Figure 30 is a schematic representation of the movement of the micro-mirror in relation to the fiber. Figure 31 is a schematic diagram of optical coherence tomography in the polarization-sensitive spectral domain based on the individual channel fiber with an optical fiber spectral polarimetry instrument (FOSPI).

Figure 32 is a schematic representation of an optical coherence tomography of a spatially scaled multiplexed source based on the fiber. Figure 33 is a schematic representation of a multi-fiber angular domain OCT. Figures 34 and 35 are images recorded with a spatially multiplexed OCT system. Figures 36 and 37 are the phase retardation due to birefringence and the fast axis angle, respectively. DETAILED DESCRIPTION OF THE INVENTION Referring now to the figures in which like reference numbers refer to similar or identical parts throughout the various views, and more specifically Figures 1-5, 15 and 16 thereof, in where an endoscope 10 for a patient is shown. The endoscope 10 comprises means 102 for producing light, such as a light source 51. The endoscope 10 comprises an array of optical fibers 28 comprising a plurality of optical fibers 8 adapted to be disposed in the patient. The array of optical fibers 28 transmits light from the producing means, preferably including a light source 51, within the patient, and transmits the light reflected by the patient outside the patient. The plurality of optical fibers 8 of array 28 is in optical communication with light producing means 102. Endoscope 10 comprises a detector D for receiving light from array 28 and analyzing the light. The plurality of optical fibers 8 of array 28 is in optical communication with detector D. Preferably, endoscope 10 includes a tube 53 around which the plurality of optical fibers 8 is disposed. The tube 53 preferably has slots 54 extending longitudinally out of the tube 53, as shown in Figure 10. One of the plurality of optical fibers 8 is disposed in each of the slots 54. Preferably, the endoscope 10 includes a probe tip 55, as shown in Figure 11, having a reflector 56 disposed in each slot that reflects light from the optical fiber 8 in the slot when the reflector 56 is on the patient and reflects light from the patient towards the optical fiber 8 when the array 28 is in the patient. The light source 51 preferably includes a coherent light source 51 and means 57 for guiding the light from the light source 51 to the plurality of optical fibers 8 of the arrangement 28. Preferably, the optical fiber 8 is an individual mode, has a center 118 with a shield 120 disposed about center 118, and has a lens 122 at its tip and focuses light from center 118 toward reflector 56 and light from reflector 56 toward center 118, as shown in the Figures 12 and 13. The array 28 preferably includes a transparent cover 7. Preferably, the light source 51 comprises an input arm 58, the array 28 comprises a sample arm 59, the detector D comprises a reference arm 60 and an arm detector 61; and the input arm 58, the detector arm 61, the sample arm 59 and the reference arm 60 together form an interferometer. Reference arm 60 preferably uses RSOD to introduce depth scanning and dispersion compensation to the interferometer. Preferably, the endoscope 10 includes an opto-coupler 62 that optically couples the corresponding optical fibers 8 of the input arm 58, the sample arm 59, the reference arm 60 'and detection arm. The detector D preferably determines the structural information about the patient from the intensity of an interference signal of the light reflected from the corresponding fibers of the sample arm 59 and the reference arm 60 having the same derivation length. Preferably, the tip of the probe 55 includes a scanning head 1 which controls the N optical fibers 8, where N is greater than or equal to 2 and is an integer, as shown in Figures 17-22c. The N optical fibers 8 are preferably arranged around the scanning head 1 in parallel and equally spaced apart.

Preferably, the probe tip 55 includes a mechanism 134 for moving the scanning head 1 such that the optical fibers 8 scan an angular range of N / 360 degrees. The movement mechanism 134 preferably includes a mechanism 9 for linear movement that causes the scan head 1 to rotate. Preferably, the linear movement mechanism 9 includes a fiber shaft support having a shaft channel 31 extending axially along the support, and N fiber channels 32 arranged around the support in parallel with the shaft channel 31. , and a threaded shaft that fits and forms the shaft channel 31, as the shaft moves in the channel, and the support rotates. The scanning head 1 'preferably has a head with a cavity that conforms to the axis and causes the scanning head 1 to rotate. Preferably, the tip of the probe 55 includes a guide wire holder 2 disposed on the scanning probe 50 that receives and follows a guide wire when the safety wire is in the blood vessel, in the biliary tract, and in the GU tract. possible. A guide wire is not necessary in the Gl tract. Preferably, the endoscope 10 includes a spring disposed between the scanning head 1 and the fiber shaft holder that forces the shaft backward after the shaft has been moved forward.

The present invention pertains to a method for photoreception of a vessel, a GU, Gl or biliary tract of a patient. The method comprises the steps of transmitting light from a light source 51 within an optical fiber array 28 comprising a plurality of optical fibers 8 in the patient. There is the step of transmitting the light reflected by the patient outside the patient. There is the step of receiving light from array 28 to detector D. There is the step of analyzing the light with detector D. Preferably, there are steps of reflecting light from each optical fiber 8 with a corresponding reflector 56 associated with the fiber, and reflect light from the patient to the fiber associated with the reflector 56. There is preferably the step of moving each N optical fiber 8 comprising the array of optical fibers 28 in an angular range of N / 360 degrees. Preferably, there is a step of applying a linear movement to cause each of the N optical fibers 8 of the optical fiber array 28 to move in an angular range. The step of applying the linear movement preferably includes the step of axially moving forward in parallel with the N optical fibers 8 a shaft threaded through a shaft channel 31 extending axially along a fiber shaft support that it has N fiber channels 32 arranged around the support in parallel with the channel of the shaft 31 which causes the support to rotate. Each of the N optical fibers 8 is arranged in a respective fiber channel 32 of the N fiber channels 32. The threaded axis is adjusted and forms the channel of the axis 31, as the axis moves in the channel. Preferably, there is the step of guiding the array of optical fibers 28 along a guidewire that is received by a guidewire support 2 when the guidewire is in a blood vessel, a biliary tract, and possibly the GU system, but Not in the Gl tract. The present invention pertains to an apparatus for studying an object. The apparatus comprises means for producing light. The apparatus comprises means for analyzing the light that is reflected from the object based on polarization, space, position or angle. The means for analyzing preferably are described in the figures, wherein the polarization is in Figure 31, the position in Figures 1-30, the space in Figure 32 and the angle in Figure 33. The present invention pertains to a apparatus to study an object. The apparatus comprises means for producing light. The apparatus comprises means for analyzing the light that has been reflected from the object based on polarization. The present invention belongs to an apparatus to study an object. The apparatus comprises means for producing light. The apparatus comprises means for analyzing the light that has been reflected from the object based on space. The present invention pertains to an apparatus for studying an object. The apparatus comprises means for producing light. The apparatus comprises means for analyzing the light that has been reflected from the object based on the angle. The present invention pertains to a method for studying an object. The method comprises the steps to produce light. The method comprises the steps to analyze the light that has been reflected from the object based on the polarizationes. , space, position or angle. The present invention pertains to a method for studying an object. The method comprises the steps to produce light. The method comprises the steps to analyze the light that has been reflected from the object based on the polarization. The present invention pertains to a method for studying an object. The method comprises the steps to produce light. The method comprises the steps to analyze the light that has been reflected from the object based on space. The present invention pertains to a method for studying an object. The method comprises the steps to produce light. The method comprises the steps to analyze the light that has been reflected from the object based on the angle. In the operation of the invention, an almost infrared broadband light source 51 sends a beam of light into the input arm 58 of the interferometer type array 28. The beam profile of the light source 51 is a circular gauss. The optics before the connector 1 make the linear beam profile and focus inside the connector 1. The interferometer-type array 28 consists of a multi-fiber-based interferometer having four fiber arms connected to an opto-coupler 62. The light incoming in the input arm 58 is divided into the sample and reference arm 59, 60, respectively. In the sample arm 59, the optical fibers 8 are distributed as an annular ring, and the light will be focused towards the target vessel perpendicular to the optical axis. In reference arm 60, RSOD introduces an in depth scan and dispersion compensation. When the reflected light from both arms remains at the same length of light path, strictly speaking within coherence length, the interference occurs. The intensity of the interference signal represents the structural information of a sample. More specifically, with respect to the input arm 58, and referring to Figures 1, 2 and 3, a single beam leaves SI and collimates through Ll. At this point, the diameter of the beam is large enough to project through all the Cl 'areas, but the beam is still circular. CLl and CL2, the circular lenses, change the beam profile to a linear shape, which means that the beam is no longer circular, but it looks narrower from Figure 2 and the shape of the beam with the beam after Ll on the Figure 3. MLl focuses all the light on Cl. This is known as an open optical solution: The light source IF has a fiber tip from which light comes out into the air. . Ll is a collimation lens 122, such that the tip of the fiber of the light source 51 should be located at the rear of the focal point of Ll in order to collimate the light. CLl, 2 are cylindrical lenses. The separation between two is the sum of each focal length of each cylindrical lens 122. These work like a telescope with a decreasing ray size in only one direction. In other words, the beam size does not change from Figure 3. MLl is a microlens array 28, which has many small lenses. Each of the small lenses is placed to have a focal point at each entrance of the Cl fiber. Cl should be located at the MLl focal point. All the micro-lenses have the same focal length. Cl is a linear fiber array 28. In an alternative mode of the input arm 58, as shown in Figure 4, known as a fiber-based solution: The light source If connected to a single-mode fiber, which connects to the fiber splitter (50:50), YES. The first fiber splitter is 1 by 2. Each output end of fiber splitter 1 * 2 is connected with a 1 * 4 splitter, SPI. Each output end of the divider 1 * 4, the second layer, is connected to another divider 1 * 4, third layer, SP2. At the output of the third layer, the fiber number is 32. The fiber 32 comprises a linear fiber array 28, SP3. Linear fiber arrangement 28: Each fiber is a fiber in individual mode, which may have a different closing frequency. The closing frequency depends on the central wavelength of the light source 51. Usually, 850 nm or 1300 nm of the central wavelength for the light source 51 is used. Each fiber is joined to another in such a way that together they form a linear fiber arrangement 28. Cl is connected to multiple interferometers. Each interferometer consists of four fiber arms and opto-couplers 62. At each end of each arm, there is a fiber connector of a linear array 28 (Cl, C2, C3, C4).

The incoming light will be divided through the optocoupler 62 in sample and reference arms 59, 60, respectively. With respect to sample arm 59, this sample arm 59, as shown in Figures 5, 6, 7, 8 and 17a, is directed to the target vessel. C2 is connected to a linear fiber array 28 which is of an angular shape at the other end. The total length of the arm will be approximately 2-3 m. When the light leaves the annular tip F, it will collimate through Ll and afterwards it will be reflected through L2 out of the probe. The reflected light from the tissue will return to L2 and L2 and will be picked up by the fiber tip. Then, two reflected lights of the sample and reference arms 59, 60, respectively, will make the interference, which will be detected by detector D of the array 28 in the detection arm. The sample arm 59 is supposed to go through the target vessel, the Gl, GU or biliary tract. C2 is connected to the linear fiber array 28 having an angular shape at the other end (probe tip 55) (Figure 8). The total sample arm length 39 ee of approximately 1.5 m. The fiber arrangement 28 will be molded through a transparent cover material 7 (for example: resin or silicone polymers). At the tip of the annular probe F shown in Figure 9, each fiber is stuck to a groove of a cylindrical polymer tube 53. The shape of each groove is shown in Figures 10 and 11. Each end of the groove has a reflector 56 which is oblique at 45e towards the axial direction. The slot will be made through the technique of micro-fabrication. Each fiber has a slow 122 at the tip, which can be manufactured by dividing a multimode fiber with a diameter of the shield 120 of the fiber individually and then melting the end of the multimode fiber in order to obtain a curvature (FIGS. and 13). When the light emanates from the tip of the fiber, the light ee will reflect outwardly through the reflector 56 at the end of the slot, and then focus on the target tissue area. The light reflected from the tissue will regress to the same path as the incoming light, and it will go to the detection arm. Micro-mechanized or micro-electromechanical systems (MEMS) and nanotechnology have become increasingly popular for the development of biomaterials and improved devices (Macilwain C, "US s large funding boost to support nanotechnology boom", "Nature, 1999; 400: 95, incorporated herein by reference.) Similar to the manufacturing methods used for computer microchips, the MEMS procedures combine the etching and / or deposition of the material and the photolithographic molding technique to de-scroll ultra-small devices (Madou, M. , "Fundamentáis of microfabrication," CRC Press: Boca Raton, 2002, incorporated herein by reference.) MEMS has been proven as promising in medicine for its small size and volume, low coefficient, and high functionality. Medicine includes an intelligent sensor for the removal of cataracts, neurolevels of the microagujae eicicon, for gene and drug distribution, and health care e DNA (Polla, DL, Erd an, AG, Robbins, WP, Markue, DT, Diaz-Diaz, J., Rizq, R., Nam, Y., Brickner, HT, Wang, A., Krulevitch, P. , "Microdevieee in Medicine," Annu. Rev. Biomed. Eng., 2000; 02: 551-76; McAllieter et al., 2000, both of which are incorporated herein by reference). However, most of the MEMS procedures are e in nature for micro-features bidi ensionalee (2D) for the processing of the eylicon material. Other micro-mechanized processes include micro-machining of the laser beam (LBM), micro-electric discharge machine (micro-EDM), and electron beam machining (EBM) (Madou, M., "Fundamentale of microfabrication ", CRC Preee: Boca Ratón, 2002), incorporated here by reference. The development of the micro-fabrication and the micro-device using metals, metal alloys, silicon, glass and polymers is described below. (Chen, S.C., Cahill, DG, and Grigoropoulos, CP, "Transient Melting and Deformation in Pulsed Laser Surface Micro-modification of Ni-P Disks," J. Heat Transfer, vol 122 (No. 1), pp. 107-12, 2000; Rancharla, V. and Chen, S. C, "Fabrication of Biodegradable Microdevice by Laeer Micromachining of Biodegradable Polymere", Biomedical Microdevice, 2002, Vol. 4 (2): 105-109 / Chen, S.C., Rancharla, V. , and Lu, Y., "Laeer-baeed Microscale Patterning of Biodegradable Polymers for Biomedical Applications", in prese, International J. Nano Technology, 2002; Zheng, W. and Chen, S.C., "Continuoue Flow, nano-liter Scale Polymerse Chain Reaction Syetem", Traneactions of NAMRC / SME, Vol. 30, pp. 551-555, 2002; Chen, S.C., "Design and Analysis of a Heat Conduction-baeed, Continuoue Flow, Nano-liter Scale Polymer Chain Reaction System", BECON, 2002, all of which are incorporated in the preend by reference. For arrangement 28, a stainless steel cylinder with a diameter of 1.5 mm is selected as the baee material. The diameter is 1.0 mm for vascular applications, larger for GU, Gl and biliary applications, and up to 3.0 mm, if desired. Both micro-grooves 54 (or micro-channel 200 micron wide) and the reflection surfaces are machined through micro-electric discharge machining (micro-ED) or micro-crushing using a mechanized focused ion tool. To improve the reflectivity of the reflection surface, the stainless steel cylinder is covered with evaporated aluminum using electro-beam vaporization.

With respect to reference arm 60, shown in Figure 14, the light is collimated through Ll after leaving connector C4, and is spectrally distributed through a lattice (Gl) and ee will focus towards a mirror (GAl) . By vibrating GAl, the length of the light path will change in order to achieve deep exploration. There are many options for building the reference arm 60 by applying existing techniques. A very simple shape of reference arm 60 has only one mirror attached to a voice coil which is conducted through a function generator with a sine wave. The light ee reflects back through the mirror and the eepe's poem or changes the length of the light path. The change in path length provides the depth scan of the target tissue because interference occurs only when both arms have the same length of light path. Preferably, the reference arm 60 is more complicated than a simple one. This is called fast scanning optical delay (RSOD) which can provide fast depth scanning and dispersion compensation. The ray of type linear array is launched from C4 and colima through Ll. A mirror (Ml) reflects the beam towards a grid (Gl) that spectrally distributes the broadband light source. The spectrally dielectric light will focus on a Galvono scan (GAl) through the lenses (L2). The separation between Gl and L2 determines the amount of chromatic degree of dierence so that any die scattering of material can be compensated for to be usually per fiber. The compensation of the ray from the center of the scanning phase determines the frequency of the edge that will show after the interference of two reflected lights. The reflected light of GAl goes to L2, Gl and to M2. And then the light reflected back towards the incoming path and will be coupled back to C4. Referring to the detection arm, as shown in Figures 15 and 16, the light is collimated through Ll after leaving the C3 connector, and is circular. The combination of CLl and CL2 makes the beam look linear in a (horizontal) plane. The array of microlenses MLl causes the light to focus on the detector D of the array 28. As shown in Figures 17, 17a, 19a, and 19b, the scanning stage 50 is comprised of a scanning head 1, a fiber shaft support 3, a threaded shaft 4, a tranepable tire 7, a guide wire support 2, and a mechanism 9 for linear movement. In this embodiment, the scanning head 1 is adapted to maintain a lot of fiber to contain optical fibers 8, which are disposed around the scanning head 1 in a parallel and equal spacing. In operation, each of the fibers is set to explore an angular range of 18 degrees (360s? - 20 - 182). The reflector surfaces 11 are formed on the scanning head 1 and are oriented at 45s towards the central axis of each respective optical fiber 8, in such a way that it can guide the light from the fiber group and direct the light through the cover transparent 7. The scanning head 1 is designed to provide 18 degrees of reciprocal rotation. The reciprocal rotation performs the scanning function required by the OCT system. The mechanism of this reciprocal rotation is described below. The fiber shaft support is substantially a tubular-tubular structure. It is formed with an axis channel 31 extending along the central axis of the fiber shaft support and 20 fiber channels 32 arranged around the fiber axis support 3 in parallel. The optical fibers 8 extend through the respective fiber channels 32. The axis channel 31 has a round transvereal area. At the upper end of the shaft channel 31, the channel of the shaft 31 is an opening, but the geometry of the opening ee reduces from the round traneverse area to the rectangular transverse hole 311. The reason for this structural design will be described together with the deepening of the threaded shaft 4. The threaded shaft 4 It has a rectangular tranevereal area, which is identical in geometry to the transvereal rectangular hole of the fiber support-axis 3. It is indicated by this name, axis 4 is partially screwed along the central axis of the axis and can be divided into a part not twisted 41 and a twisted part 42. In the assembly, the shaft 4 passes through the transvereal rectangular hole of the fiber-axis support 3, and is enabled to slide reciprocally through the rectangular transverse hole. The relative movement of the surface of the tranevereal rectangular hole and the threaded shaft 4 from the mechanism that performs the reciprocal rotation. The reasons that when the twisted part 42 of the shaft 4 slides through the rectangular transverse hole, the shaft 4 itself is forced to rotate along the central axis of the shaft to adapt and coincide with both surfaces of the rectangular transverse hole and the threaded shaft 4. Particularly, the shaft 4 and the support 3 compose a mechanism 9 that can transmit a linear movement in a rotational movement. The description now focuses on the scanning head 1. The scan 1 has a rectangular recess 12, which has a cross-sectional area identical to that of the screwed-in axis 4. The rectangular recess 12 provides a channel covering the non-twisted part 41 of the axis screw 4 and leave the non-twisted part 41 exerting the reciprocal movement within the rectangular recess 12. The range of movement of the spindle 4 is limited such that the twisted part 42 does not pass into the rectangular recess of the scanning head 12 ( this will result in a geometric mismatch, but the twisted part 42 only interacts with the rectangular traneversal orifice of the fiber-axle support According to the previous decree, the movement of the axis 4 is comprised of a linear component (V) and an angular component (co) referring to the geometry of the rectangular gap 12 and the non-enroled part 41 of the axis 4, the linear component of the axis movement (V) it will not contribute to the movement of the scanning head 1 (independent of the friction between the surface), but the angular component (?) does so. The scanning head 1 rotates reciprocally with the rotational movement of the threaded shaft 4, which in turn results from the reciprocal linear movement of the threaded shaft relative to the support of the fiber-axis 3. As re-examined, the scanning head 1 provides a reciprocal rotational movement tranemitted from the reciprocal linear movement provided by the threaded shaft 4. A guidewire support 2 is a module used to guide the scanning probe 50 towards the investigated section of the detected blood vessel, the bile duct, and possibly the GU application. For the Gl tract, a guide wire is usually not used. In operation, a guidewire 01, or "guidewire", is previously arranged along a specific pathway of the human blood vessels, so that a pieta can be formed for the scanning probe 50 of the OCT system. The support of the guide wire 2 limits the scanning probe 50 in such a way that it can only be slid along the track formed by the guide wire 01. The scanning probe 50 is consequently guided towards the ejection of the patient who is will inveetigar. The support of the guide wire 2 and the support 5 function as a bearing of the scanning head 1. They limit the movement of the scanning head 1 and stabilize it. Also, a compression spring 6 is disposed between the scanning head 1 and the fiber-axis support 3. The spring 6 is moderately compressed in the assembly., in such a way that it pushes the scanning head 1 against the support 5 and eliminates any potential axial movement of the scanning head 1 which can re-propel in axial positioning errors (? d). It is preferred that the spring 6 supply twisting force between the scanning head 1 and the fiber-axis support 3. The spring 6 has its both ends, respectively, fixed to the scanning head 1 the fiber-axis support 3. The reeorte 6 is moderately threaded in the assembly. By these means, the spring can provide a twisting force to the reciprocal rotational mechanism, such that the kickback (resulting from, for example, the tolerance between the rectangular transverse hole and the shaft) of the rotational mechanism, as well as the angular positioning resulting (??), ee eliminate. Note that the transverse geometry of the axis 31 channel is circular. With respect to the channel of the shaft 31, the threaded shaft 4 is formed with a cylinder part 43 at its end of the threaded part 42. The part of the cylinder 43 and the channel of the shaft 31 carry out the piston-like movement. In an upward movement of the threaded shaft 4, due to the geometrical difference, the part of the cylinder 43 will lock at the end 33 of the rectangular tranevereal hole of the fiber-axis 3 support and will provide an upper stop for the threaded shaft 4. For the On the other hand, a lower stop 34 is placed to block the part of the cylinder 43 in the downward movement. The function of the upper and lower stops is useful in controlling the movement of the threaded shaft 4, as well as to control the angular movement of the scanning head 1. There are many methods in the prior art that are capable of providing the energy that the mechanism Push and pull the threaded shaft 4 to generate the linear movement. However, hydraulic force, particularly fluid pressure, is preferred because of the following advantages: 1. Electricity is not required to be transmitted within the scanning head 1 to give power to the hydraulic linear mechanism 9. Some of the Mechanisms, such as the electromagnetic sevenmae (or more particularly, some micro-motors), require not only electricity to be energized, but also additional components, for example, coils or magnets, in-line in the scan head 1 to transform electrical energy in a mechanical moment. The use of electricity is not preferable for weaves raedicoe; and the requirement of additional component could increase the technical difficulty in the manufacture and complexity of the complete system. Some of the other mechanisms, such as those that comprise piezoelectric materials, can eetar compounds with a small space and a simple structure, but still need to receive a large voltage to generate the required moment. 2. A hydraulic mechanism 9 occupies little space. The structure of the hydraulic mechanism 9 is illustrated in Figures 18a and 18b. The hydraulic mechanism 9 can simply be a liquid conduit that guides the liquid, such as water, to push or pull the piston system comprised of the part of the cylinder 43 and the channel of the shaft 31. Considering that the leakage through the recess of the Piston system can result in undesirable problems, the hydraulic mechanism 9 is preferably comprised of a micro-balloon 91 made through a thin polymeric film. As shown in Figures 18a and 18b, the threaded shaft 4 is in its lower position when the balloon 91 is flat (Figure 18a). Since water is pumped into the pincushion, the balloon 91 is inflated, and the threaded shaft 4 is pushed toward the euperior position with a 18 degree turn (Figure 18b). The required reciprocal movement can be generated by exchanging the flat-to-balloon states of the micro-balloon 91. For a seventh OCT of a fiber, the scanning degree of 6 rev / sec (6 Hz) is satisfactory [Andrew M. Rolling and others, "Real-time in vivo imaging of human gastrointestinal ultrastructure by uee of coherent optical endoscope tomography with a novel efficient interferometer design", OPTICS LETTERS, Vol. No. 19, October 1, 1999, incorporated by reference in the preamble]. This means that a second the seventh OCT should be able to provide at least 6 photographs that illustrate the transverealee data of the vessel. The scanning probe 50 has 20 fibers, such that the satisfactory degree of scanning can be reduced to 0.3 Hz (6-5-20 = 0.3), which is much slower and much easier to carry out through the seventh. of hydraulic activation. Ideally, 15 photographs / second are required for an optimal image re-evaluation. Instead of the continuous rotation, the scanning probe 50 operates in a reciprocal manner, such that the angular velocity of the scanning head 1 will not be a constant even when the entire system reaches its eetable state. During the operation, therefore, the detection of the angle of the scanning head 1, as well as the calculation of the angular reading of which the data belong to, are important aspects. The angle of the scanning head 1 can simply approximate by comparing the output effort with the pumping system with a reference curve obtained from previous experiments. The most accurate detection can be achieved through the analysis of the feedback of the optical signals. For example, the analysis of the Doppler effect of light [Back Weetphal et al., "Real-time, high velocity-reeolution color coherent optical Doppler tomography", OPTICS LETTERS, Vol. 27, No. 1, January 1, 2002, incorporated by reference in the preend] of the feedback signals is another method. The threaded shaft 4 can be formed by means of precise CNC machining which is well known in the industry. A thin round shaft, with a minimum diameter of 1.0 mm, can be used as the intrinsic material before machining. For production, two ends of the round shaft are secured, its central portion is precisely ground and four orthogonal planes of the central portion are generated. The planes define the transvereal rectangular section of the threaded shaft 4 (forming a large axis in this step), as shown in Figure 20a. After the crushing, one of the two clamps that support the shaft is rotated relative to the other clamp to screw the shaft to a specific angle around its central axis. The threaded part of the threaded shaft 4 is formed. After the step of screwing, the rotated clamp is released to release the elastic distortion of the shaft (with its remaining plastic depot), and then remove the clamp from the clamp again. In the next step, as shown in Figure 20b, the axis is again shredded on one side of the still-round portion, thereby generating another rectangular portion that is einá ein enroscar. The cylindrical portion (serves as a piston) is formed from the round portion of the shaft. An accurate suturing could also be used to fix the central axis and the diameter of the cylindrical part. As shown in Figure 20c, only a short portion of the shaft is required. The excess portion of the shaft part is trimmed. As shown in Figure 21a, the fiber-axis support 3 can be combined with two parts, A and B. The part A is currently the body of the catheter. The transvereal section of the catheter is shown in Figure 21b; The catheter could be manufactured using a cable extrusion technique that is generally applied in the fiber optics industry (refer to the Optical Cable Corporation page.) Note that the central channel of the catheter is used to be the conduit for the guidance of the catheter. The aforementioned activation liquid There are also several conduits that are used to guide the air that flows in and out of the tip of the probe to balance the air pressure within the OCT system (during operation, the free volume within the The tip of the probe changes as the threaded shaft 4 moves.) The diameter of the conduit is equal to that of the cylinder part 43 of the threaded shaft 4. Part B in Figure 21a is simply a plate having fiber support edges. (Bl) and a rectangular central opening (B2) .This part could be made of metal using the puncture technology as it is commonly applied in the industry. e part A and part B are connected with glue such as epoxy. The lower stop, which is required to restrain the threaded shaft 4 in its lower position, forms together with the formation of the micro-balloon. Micro-molding with polymeric material (such as SBS) could be used to manufacture the scanning head 1. The micro-molding process requires a micro-mold group. In this case, the groove of the fiber 54 and the reflective surface 11 at the end of the fiber groove 54 can be carried out through a group of micro-molds comprised of 18 edges (Figure 22a), each those with the geometry shown in Figure 6b. Also, the central rectangular channel could be molded through a rectangular shaft made through the equipment for making the threaded shaft 4. For the convenience of the eneamble, the scanning head 1 could previously provide with the geometry shown in Figure 22c. The portions in excess of the scanning head 1 could provide guidance and aid in the alignment of the optical fibers 8. The UV compensation could be used to fix the laser fiber optic portion 8. The excess portion of the scanning head 1 could cut off after the fiber optic bundle 8. In another embodiment, the heat rays heat at least different places on the surface of the mirror micro-210, which is shown as a disk in Figures 23-25, successively. The micro-mirror 210 will provide a corresponding wobble for this kind of asymmetric heating process, and an incident light (other than the heating lamp) can be redirected in a wobble form. This heating procedure corresponds to the rotation period of the micro-mirror 210 as required.

The micro-mirror 210 comprises two layers: a first layer 212 and a second layer 214 (Figure 23). At least one of the two layers can generate structural deformation (contraction or expansion) through the application of the laser light. If the layer in which the layers are deformable through the laser light, the availability of the two layers to the same laser light could be differentiated between them. FIG. 24 shows the vieta in perspective of the microwell 210. When the microwell 210 is irradiated with a laser beam, there will be an expansion or contraction in the layers. Due to the expansion or contraction within the layers is of different degrees (only one layer is deformed or the two layers are deformed with different degrees), the structure of the complete micro-mirror 210 will deform. For example, in Figure 25, when the section marked with the cake is irradiated with a laser beam, a strain generated as shown in Figure 26 is exempted. The material of the first and second layers 212, 214 could be metal or polymer. photosensitive In the case of metal layers, for example, the first layer 212 is poly-silicone and the second layer 214 is gold. The mechanism of expansion or contraction within the layers is thermal expansion. The metals will absorb energy from a laser beam and will heat up. Due to the different coefficients of thermal expansion of the layer, the structure will be eroded or flexed. This will result in the rotation of the mirror, as shown in Figure 26. In the case of photoenerable polymer, for example, liquid glass material, the mechanization of the expansion or contraction within the layers is a phase change of the layers. materialee. Under the irradiation of the laser beam, the molecules of the polymeric matter will undergo the change of fae, where the chemical structure of matter is deformed, and structural deformation occurs. Next, similar to the case of the metal layers, the degree of deformation of the layers is different, and there will be a kinking or bending effect on the structure of the micro-mirror 210, and the effect in Figure 26 is achieved. When the structure is twisted or flexed through the application of laser energy, the surface of the mirror, shown in Figure 24, can be tilted to a specific direction. Accordingly, the direction of micro-eject 210 can be controlled by controlling the input of laser energy. The way of controlling the application of the light is to select the location of the micro-mirror 210 to be irradiated by means of the laser beam, and to control the intensity of the laser. By controlling the location, you can control the direction of inclination of the mirror; and by controlling the intensity, the tilt angle of the micro-mirror 210 can be controlled. Referring to Figure 25 and Figure 26, by continuously changing the location of the laser brightness (Figure 27), the tilt direction of the micro-mirror 210 can change continuously (Figure 28). That is, the micro-eject 210 could rotate by changing the location of the laser brightness. This is the mechanism for the rotation of the laser-activated micro-epee 210. As for the assembly of the complete OCT system (Figure 29), the micro-mirror 210 is mounted on a base 21b connected to the end of the tip of the cover. the probe. There is no effect between the fibers and the mirror. The fiber 1, which is used to guide the detection light, is the same fiber used in the other modalities of the OCT probe. The detection light is redirected through the inclination surface of the micro-mirror 210, so that it can scan around by means of the inclination and rotation of the mirror. The fibers 2 are used to guide the laser-activated light. As shown, at least three fiber 2 are needed. The fibers 2 fire lasers in turns, in such a way that they can generate a continuous tilt effect as shown in Figure 27 and Figure 28.

The other characteristics of the laser activation OCT probe are the same as those described in the other modalities. For example, fiber, and fibers 2 are arranged on a fiber shaft support 3. After manufacture thh the eemiconductor technique, which is well known to those skilled in the art, the mirror is formed on a substrate (usually eilicón euetrato). The substrate material forms the base. Then cut a small piece of the base that takes the eetrato of the euetrato with a slicer. The small piece is mounted on the end of the tip by means of glue (epoxy, for example, only one fiber 1 is sufficient to transmit the detection light in this mode.) During the operation, a circular scan profile is carried out of the detection laser In this embodiment, illustrated in Figure 30, the detection laser is not centered in the center of the mirror, rather, the following remains constant: (1) d, the distance between the center of the mirror and the axis of the detection light. (2) alpha, the angle between the mirror surface and the axis of the detection light. An open cycle seventh is used to place the feedback to appropriately distribute the periodic change of the laser energies from lae three fibers 2 to carry out the constant alpha and d.

The control of positions more complex than the activation of the individual fiber 2. Particularly, the micro-mirror 210 needs a period of time to respond mechanically to the laser energy coming from the fiber 2. Even when it is known when and which of the lae 2 fibers trigger the laser energy, the exact direction of the information of the mirror surface can not be ensured. The absolute position of the mirror is currently not necessary. Rather, speed-control is used to control the rotation of the scanning mirror. For example, in the case of the mirror driven by a transmission cable rotated from the outside, the exact position of the mirror (which may be affected by a delay in the transmission of the cable due to acceptance of the cable) is not of concern; the period of rotation of the mirror is controlled in such a way that the "relative position" of the mirror is known. After receiving a stream of continuous data from the reflected detection laser, the transverse image of the vessel is constructed simply by comparing the data series with the rotation period. In this mode, the operation will be similar. What is different is that the micro-mirror 210 is not activated thh a propeller but thh three deformable cantilevered beams with bimorph heat. This makes the control more complex. If only one of the fibers 2 shoots at the same time, it will be very different if it is not possible for the team to explore a necessary profile. Rather, the three fibers 2 are needed to fire together, with different energies, to flex the tree racks in different directions simultaneously to coincide with a circular scanning profile. The tree baetidoree are activated individually thh tree fiber 2 in such a way that they cooperate with the specific bending patterns that make a circular exploration profile on the wall of the vessel. In an alternative embodiment with respect to the microwell 210, the fiber 1 and the fibers 2 ee invert so that the healing energy comes from one fiber 2 disposed preferably along the central axis of the tube. The plurality of fibers 1 is arranged ad the circumference of the tube. When the micro-mirror 210 is irradiated thh the laser beam from the fiber 2, the laser energy causes the mirror to flex. By changing the intensity of the laser or pressing the laser, the movement can be imported into the micro-mirror 210 which wires the tip of the probe to which it is attached, to reciprocate, and in this way the plurality of fibers 1 to explore the interior of the patient's area in question. The thermal expansion material can usually generate -5% elongation for a high temperature of 100SC. The length of the material inside the OCT is originally 20 mm, which can therefore generate a thermal elongation of 1 mm. Polymers, including photosenetable polymers and shape memory polymers, are capable of generating more than 100% of the elongation or photo-induced shrinkage. The material inside the OCT was originally 1 mm, which can consequently generate a thermal elongation of another 1 mm. Generally: Optical tomographic imaging can be specified through the spectrally resolved bandwidth, equivalent to the number of spectrally resolved cells. Each spectrally resolved cell has a width dv, such as the number of cells resulting from the instrument ee where the available optical bandwidth of the light source is seen. The group-time delay range that the optical tomographic instrument can solve is given by: The smallest resolvable time-group delay that the optical tomographic instrument can solve is? TCOherence = l /? V. The number of cells speci fi cally re-evaluated that the optical tomographic instrument can solve is given by: Instrument = A ^ ins truncate / ^ coherence • For an OCT scan within the object being photographed, the requirement for a speci fi cally reelectable cell number is Le ~ cg /? V,? Z = depth of photoreception, Lc ( coherence length), and cg is the speed of the light group in the object. NA-exploration - ATA-e? Pioration ^ V Where? TA.expioration =? Z / cg is the round trip propagation time for light to propagate from the most euphemial to the deepest poetry (which is going to be photo-received) in the object. For some tomographic and optical photoreceptor inputs (for example, those using narrow line width tuneable sources or high-resolution spectrometers), Nins truncate / > > 1 The above condition can be manifested in tree formae: a) the number of cells eepectrally referenced for the instrument (N instrument) is much greater than that required for an A exploration (NA-eXpioration); 2) the range of group time delays has instrumentation capable of solving (? Tinstrumeno) is much greater than the group-time delay for a single exploration A (? TA-e? Pioration); 3) optical bandwidth available for the light source (? V) is much greater than the spectral width of each reeoluble cell of the inetrumentation (dv). Because the instrument can solve much more cells than are required for an A scan, the multiplexing techniques are presented here to efficiently use the information carrying capacity (bandwidth) provided by the optical tomographic photoreceptors. The selection of the criterion for the multiplexing techniques used can be derived in part through the relation N-instrument A-exploration-Tinstrumen or? TA-expioration =? V / dv. The larger relationships provides a wider selection of possible multiplexing techniques and candidate domain (polarization, space, angle, temporal) to carry out multiplexing. In addition, multiplexing spectral information in only one domain (for example, spatial) is not the only method displayed. Generally, additional spectral information can be reelected in multiple domains (eg, polarization and spatial). Specific Implementations: A. Polarization: Additional spectral cells can be used to record the information in the polarization domain using a system indicated in Figure 31. At least two incident polarization features are captured at 90 * apart from the Poincare sphere in the interferometer. Identification of the polarization of light reflected from the parent, such as a vessel wall or fibrous layer of the nerve, is compared to known polarization identifications of materials, such as plaques or a fibrous layer of diseased nerve. The reflected light and in this way the material from which it is reflected is identified. The fiber distribution system described in PCT patent application No. PCT / US2004 / 012773, incorporated by reference herein, may be used. The theory of the operation of this method is described using the Mueller matrices or the Jonee calculation, which is re-speculated. By inerting a FOSPI in the detection path of the optical coherence tomography imputation of the spectral domain (SDOCT), the complete set of Stokes parameters of back scattered light at a specific depth in the specimen can be obtained without any other component that controls the polarization in the reference trajectory / sample / detection of the interferometer and the previous knowledge of the polarization state of the light incident in the sample. In this configuration, two factors determine eepectral modulation. One ee the optical path length difference between the reference and the parent surface, (? (V)), introduced by the common path SDOCT and the other is the phase retardation, Fl (v) and F2 (v), generated through the retarding system in FOSPI. Accordingly, the polarization output of the individual presented sensitive (PS) SD-OCT channel in the time domain of the delay is the circumvolution of the FOSPI ealide, and that of SD-OCT. The Stokes parameters of light at the output of the interferon eon: Si = Si,? + Si, 2 + Si, i where the first two terms are the Stokes light parameters of the reference path and of the reflector, respectively, and the last term ee the contribution of the interference. To connect the sample of double refraction with phase retardation d and the fast axis oriented in the angle of. Next, the Stokes parameters of the sample light (S?, 2) and the interference Si, i) are calculated in terms of the Stokes parameters of the reference light, S0,?, S?,?, S2, ?, S3,? S0.2 = r.? S0, l If 2 = r (cos2 2a + cos¿sin22a) Su + r2 (l-cost5) sin2acos2ß¡Sl2 ?? -r¡ svadsxalaS ^ (1) S22 = r (1 - eos d) without 2a eos 2 < 2- ?, j + /; 2 (sin22a + eos icos2 2a) S2 j + r without d without 2cSi X S32 -rj¡ without < 5 if 20 $], -r without <5cos2o5'2 ,? +? cos? 3] S0 i = 2rs cos? cos (eos 2? Sl? + without 2aS, 2 1) S \? ~ 2? "s cos? (cos - S, j - sin - without 2oS3 l) + 2r, sin? sin - eos 2a5O.}. (2) S2j ~ 2rs eos? (cos - S2 + sin - sin 2aS3 j) + 2rs sin? Sin - eos 2 SQ S?? * S t¡ - 2rs cos? (Sin- sin2aS, 1 1 -sin- cos2aS2 1 + cos- S3 j) 2 * t with a reflection coefficient of the sample rs and an optical path length difference between the sample and reference trajectory?. Here, the terms include the trigonometric functions of? which represents the interference between the light of the reference and sample path. The measured inteneity of the SDOCT that paea through FOSPI for a sample of double refraction, then it is: d d 1 'out, i () = rs C0S? COS EO! + rs s * n? sin- (eos 2a¡_> 1> j + s? n2a52,?) ddd (eos- JSJ J - sin- sin2a5S3j?) cos (? - fz) + sincos2c &S, 0 1 sm (? - f2) 2 s COS2CBS, 0) 1 sin (? + < p2) dd (eos- S2¡ \ + sin- cos2avS3 1) cos (? - f2 + f) 4 sddd +. { sin - sin2Gr (»S'0jl + S ^) - sin - eos 206 * 2 j + cos, S3 # j} s? n (? - f2 +? \) 1 d d (cos-S2¿ + sin - cos2aS'3 1) cos (? + f2 - f) • '3) 4 s d d d +. { sin - sin2a (S'0 j - Sx j) + sin - cos2osS2s? - eos- S3 > 1} s? n (? + f2 - fx) \ \ d d ~ rs \ (cos-S2? + sin - cos2ai? 3?) cos (? - f2 - f) d d d +. { sin- sin2a (? S'0 1 + S? j) + sin- cos2a-S, 2 ?? - eos- 53 > ? } sin (? - f2 - f 1 [dd - rs (eos - S2, + sin - COS2? -S'3 1) COS (? + f2 + f) ddd + { sin - sin2a (? SO, + St l) - sync2ceS2 i + eos- ¡S ^ j.}. sin (? + f2 + f) for the interference signal. The Fourier transformation of equation (3) gives seven components in the domain of the optical path length difference that are centered on?,? ± F2,? ± (F2-F1),? ± (F2-F1), reepectively. The Fourier invertae formations of each component are as follows. í d d 1? -jr,. * eos- 50jl - i sin- (cos2e? S'1 1 + sin 2cß2, i) ¡(4) + < 5) d d d - ¿. { sin-sin2a (S0 1 + Si) - sin-cos2aS, 2 1 eos- S3 1} (7) Comparing with equation (2), the real part of equation (4) gives S0,? / 4, and the real part of the equation of (5) deepuée of exchanging faee by -F2 gives Si, i / 8. Likewise, S2, i / 8 and S,? / 8 can be obtained by taking the part of the derivation of (7) from (6) and the photoreceptor part of the addition of (6) and (7) after the exchange phase appropriate - (F2-F?) and - (F2 + F?) by (6) and (7), respectively. In addition, simple arithmetic gives the phase retardation due to the double refraction of the sample, d, without knowledge of the incident polarization state. The real part of (4) the imaginary part of (5), the imaginary part of the subtraction (7) of (6) are: 1 d. ~ rs eos-So ,! (8) I £ - rv sync2csS0? (9) 4 s 2 ° '1 after the exchange of faee through -? - (? + F2), - (? + F2-F?) And - (? + F2-F?), Respectively. With a trigonometric identity, you can obtain the following: Phase retardation due to double refraction [Figure 36] and fast axis angle [Figure 37] of the double refractive sample were estimated from the interference between the rear surface of the glass window and the rear surface of the double refractive sample using the previous equations. For this measurement, the double refraction sample was rotated in increments of 5S to 9 / s. An estimated one-step phase retardation of 34.06s ± 2.68a is consistent with a value deduced from the manufacturer's specification (31.4S). The estimated fast axis angle is shown in Figure 4 (b) and the graph with respect to the orientation of the double refraction wheel. The results show a practical demonstration of polarization multiplexing. B. Space or Lateral Position: The spectral cells Additional items can be used to record the information in the domain of the space or side position using the seven-fold indicated below. 1. Existing Multifibre method:. { described above) 2.- Spatially Explored Light: The schematic of the experimental configuration of a spatially multiplexed, fiber-based scanned source OCT system (SM-SS-OCT) is described in Figure 32 using the sevenma described in the patent application PCT No. PCT / US2004 / 012773, incorporated by reference herein, wherein the top portion is preferably rotated at least 100 times for each position. A tunable laser and a spectrum analyzer (TLSA 1000, Precision Photonics, Inc.) operating in the wavelength range of 1520-1620 nm (? 0 = 1570 nm) with a specified spectral line width F HM at 150 KHz is used as the source of illumination and is equipped with an optical insulator to protect the laser from false reflections. The laser output is coupled to an arm of a 2 x 2 fiber-based coupler (interferometer). The 50% -50% coupler divides this beam into two almost equal parts, used in the reference and sample arm, respectively. The reference arm has a fixed path length, and simply consists of a fixed mirror that reflects the incident of full light when it returns to the fiber-based coupler. The light coming out of the arm of the interferometer from the collima and is scanned through the scanner through a scanning galvanometer and focusing lenses. The scanning galvanometer and the focusing lenses are used to quickly explore the lateral positions of the tissue. The TLSA 1000 completes a full wavelength sweep in approximately 1 second. Within this time, the galvanometer is programmed to sweep all the lateral positions of the fabric several hundred times. The light returning from the sample interferes with the light of the fixed reference on the fiber-based interferometer, and the referenced eepectral interference signal (due to the variation of the path length between the reference and reference reflexe) and detects through a photodetector placed on the detection arm of the seventh. The electrical output is digitized, and a non-uniform Fourier trait (NUFT) of each spectral data of line A gives the depth profile of the reflectance of the sample. The fibers 34 and 35 are images of a poetry area with a groeor of 100 microns recorded with the spatially multiplexed OCT system. The images are of the same object (glass cover of the microscope) only for one image (Figure 34) the intensity of the light returning from the sample is displayed in linear grisee scale while in the other image (Figure 35) it is displayed. according to the logarithm of the intensity. C. Angle: The additional spectral cells can be used to record the information in the angle domain using a system indicated in Figure 33. Figure 33 describes an OCT multi-fiber angle domain system. The output of the frequency sweep source A is divided into n fibers through the divider B. The light paes through the circulars C, collimates, focuses through the lenses, comes into contact with the tissue, and then it is reflected within any of the multiplicity of fibers. A reference reflector for each path is introduced into each fiber segment. For example, the reference reflector can be placed at the terminal end of each fiber segment. For each input fiber segment, the interference is formed between the backscattered light from the fabric and within the fiber j, and the reflection of the reference from the fiber j, avo. The N fibers, the N2 interference edges are each formed corresponding to an incident (oti) and the backscattered angle (ßj). The inteneity of the light in the eepectral domain is converted into a voltage across a photoreceptor, which outputs a large ADC, which is read by a computer. This eietema allows the resolute photoreception of the angle necessary to the discrete light path fae inside and outside the specimen. By using spatial-spatial frequency transformation (bidimeneional Fourier transformation), lateral structures can be photorecepted with sub-wavelength feedback. D. Space-angle combinations (for example, dimension-space, and dimension - angle): The dimensions of space and angle can be combined to form systems that use the image of additional spectral cells of both space and angles. For example, the additional spectral cells may be used to record the position information in one dimension (for example, x) and the angle information in the orthogonal dimension (y). Although the invention has been described in detail in the above modalities for the purpose of illustration, it is understood that said detail is only for what is proposed and that the variations can be made herein by those skilled in the art without departing from the spirit and scope of the invention except as may be prescribed through the following claims. It is noted that in relation to this date, the best method known to the applicant to carry out the aforementioned invention, which is clear from the present description of the invention.

Claims (34)

1. CLAIMS Having described the invention as above, the property contained in the following claims is claimed as property: 1. An endoscope for a patient characterized in that it comprises: a light source; Means to produce light; a fiber-optic array comprising a plurality of fiber optics adapted for ee diepueetae in the patient, the fiber optic array trades the light from the light source within the patient, and tranects the light reflected by the patient out of the patient, the plurality of fiber optics of the array in optical communication with the light source; and a detector for receiving light from the array and analyzing the light, the plurality of fiber optics of the array in optical communication with the detector.
2. 2. - An endoscope according to claim 1, characterized in that it includes a tube around which is arranged in the plurality of optical fibers.
3. 3. - An endoscope according to claim 2, characterized in that the tube has grooves extending longitudinally along the tube, a plurality of optical fibers dispueeta in each of the grooves.
4. 4. - An endoscope according to claim 3, characterized in that it includes a probe tip that has a die reflector in each slot that reflects the light of the optical fiber in the slot when the reflector is in the patient and reflects the light from the patient to the fiber optic when the fix is in the patient.
5. 5. - An endoscope according to claim 4, characterized in that the light source includes a tunable light source and means for guiding the light from the light source to the plurality of optical fibers of the array.
6. 6. - An endoscope according to claim 5, characterized in that the optical fiber is individual mode, has a center with shielding arranged around the center, and has lenses at its tip that focus light from the center towards the reflector and light of the reflector towards the center.
7. 7. - An endoscope according to claim 6, characterized in that the arrangement includes a transparent cover.
8. 8. - An endoscope according to claim 7, characterized in that the production means comprise an input arm, the array comprises a sample arm, the detector comprises a reference arm, and a detector arm; and the input arm, the detector arm, the sample arm and the reference arm together form the interferometer.
9. 9. - An endoscope according to claim 8, characterized in that the reference arm uses RSOD to introduce the depth scan and the dispersion compensation to the interferometer.
10. 10. An endoscope according to claim 9, characterized in that it includes an opto-coupler that optically couples light from the input arm to the corresponding optical fibers of the sample arm.
11. 11. An endoscope according to claim 10, characterized in that the detector determines the structural information about the patient from the intensity of an interference signal from the reflected light of the corresponding fibers of the sample arm and the reference arm. .
12. 12. - An endoscope according to claim 11, characterized in that the tip of the probe includes a scanning head that controls the N optical fibers, where N is greater than or equal to 2 and is an integer.
13. 13. - An endoscope according to claim 12, characterized in that the optical fibers N are disposed around the scanning head in a parallel and equal spacing.
14. 14. - An endoscope according to claim 13, characterized in that the tip of the probe includes the mechanism for moving the scanning head in such a way that each optical fiber explores an angular range of 360 / N degreee.
15. 15. An endoscope according to claim 14, characterized in that the movement mechanism includes a mechanism for linear movement that causes the scanning head to rotate. An endoscope according to claim 15, characterized in that the linear movement mechanism includes a fiber shaft support having an axis channel extending axially along the support, and the N fiber channels are arranged around of the support in parallel with the channel of the shaft, and a screwed shaft that adapts and forms the channel of the shaft, according to the threaded shaft moves in the axis channel, the support rotates. An endoscope according to claim 16, characterized in that the scanning head has a head with a cavity that conforms to the axis and causes the scanning head to rotate. 18. An endoecope according to claim 17, characterized in that the tip of the probe includes a guidewire support in the scanning probe that receives and follows a guidewire when the guidewire is in a bloodstream, biliary tract and possibly GU. An endoecope according to claim 18, characterized in that it includes a re-inserted die between the scanning head and the first axis support that forces the return shaft after the axis has moved forward. 20. An endoscope according to claim 3, characterized in that it includes a light-activated material that turns at least a portion of the tube when light is received by the light-activated material. 21. A method for photoreception of a patient's vessel, characterized in that it comprises the steps of: transmitting light from a light source within an array of optical fiber comprising a plurality of optical fibers in the patient; transmit the light reflected by the patient outside the patient; receive the light from the array in a detector to translate the signal; and analyze the light signal with the processing element. 22. A method according to claim 21, characterized in that it includes the objects of reflecting light from each optical fiber with a reflector associated with the fiber, and reflecting the light from the patient to the fiber associated with a reflector. 23. A method according to claim 22, characterized in that it includes the step of moving each of the N optical fibers comprising the array of optical fibers with an angular range of 360 / N degrees. 24. A method in accordance with the claim 23, characterized in that it includes the step of applying a linear movement to cause each of the N fiber optics of the optical fiber array to move in an angular range. 25. A method in accordance with the claim 24, characterized in that the step of applying the linear movement includes the step of moving axially forward in parallel with the N optical fibers a shaft threaded through the shaft channel extending axially along the support of the fiber shaft having N fiberglass canalee diepueetoe around the support in parallel with the channel of the shaft that causes the support to rotate, each of the N fiber optics dispueeta in a respective fiber channel of N fiber canalee, the axis enroecado ee adapts and conforms the channel of the axis, according to the axis ee moves in the channel. 26. A method according to claim 25, characterized in that it includes the step of guiding the fiber optic array along a guide wire that is received by a guide wire support when the guide wire is in a blood vessel, tract. biliary and possibly GU. 27. An apparatus for studying an object characterized in that it comprises: means for producing light; and means for analyzing the light that is reflected from the object based on polarization, space, position or angle. 28. An apparatus for studying an object characterized in that it comprises: means for producing light; and means to analyze the light that has been reflected from the object based on polarization. 29. An apparatus for studying an object characterized in that it comprises: means for producing light; and means to analyze the light that has been reflected from the object based on space. 30. An apparatus for studying an object characterized in that it comprises: means for producing light; and means for analyzing the light that has been reflected from the object with baee at an angle. 31. A method for studying an object characterized in that it comprises: producing light; and analyze the light that has been reflected from the object based on polarization, space, poetry or angle. 32. A method to study an object characterized because it comprises: producing light; and analyze the light that has been reflected from the object with baee in the polarization. 33. A method for studying an object characterized in that it comprises: producing light; and analyze the light that has been reflected from the object based on space. 34. A method for studying an object characterized because it comprises: producing light; and analyze the light that has been reflected from the object based on an angle. SUMMARY OF ? INVENTION The present invention relates to a system for tomographic photoreception of optical coherence of materials túrbidoe (ie, diffusion) that uses multiple channels of information. The multiple information channels may be included and encompass spatial, angle, spectral and polarization domains. More specifically, the present invention relates to methods and apparatuses for utilizing a source, an eietemae or a receiver capable of providing (source), proceeding (system) or recording (receiver) a multiplicity of spectral information channels for tomographic photoreception of optical coherence. of turbid materials. In these methods and apparatus, the multiplicity of information channels that can be provided by the source, processed by the system or recorded by the receiver, is used to simultaneously convey spatial, spectral or polarimetric information related to the turbid material that is being photographed. tomographically. The tomographic methods of multichannel optical coherence can be incorporated into an endoecoptic eonde for photoreception of the patient. The endoecope comprises an array of optical fiber and may comprise a plurality of optical fibers adapted for eer diepueetae in the patient. The fiber optic arrangement trades light from the light source within the patient, and tranemite the light reflected by the patient outside the patient. The plurality of optical fibers in the array is in optical communication with the light source. The multichannel optical coherence tomography system comprises a detector to receive light from the array and analyze the light. The methods and apparatuses can be applied for the photoreception of a patient, GU and / or Gl tract of a patient.