Abstract:
An improved endoscopic device which is introduced into the intestinal tract of a living organism and which operates autonomously therein. In a first embodiment, the probe utilizes a miniature charge-coupled device (CCD) camera and a fiber optic/diode illumination system for inspection of the intestine wall. The CCD camera operation is supported by data processing electronics and an inductive data transfer circuit located within the probe which facilitate the real-time transfer of the acquired image data out of the probe to an external monitoring and control device. Power is supplied to the probe inductively from an external power source. The probe is completely sealed so as to be protected against damage by gastric acids or other potentially damaging substances residing within the patient. A second embodiment of the probe incorporates a miniature diode laser which is used in conjunction with the CCD array to produce autofluorescence spectra of the interior of the intestinal wall. In another aspect of the invention, an improved endoscopic device useful for implanting the aforementioned endoscopic smart probe is disclosed. A method for inspecting and/or treating the interior regions of the intestinal tract using the aforementioned smart probe is also disclosed.

Description:
This application is a continuation of U.S. patent application Ser. No. 09/259,194 filed Mar. 1, 1999 abandoned entitled “Endoscopic Smart Probe and Method”, which is incorporated herein by reference in its entirety. 
    
    
     BACKGROUND OF THE INVENTION 
     1. Field of the Invention 
     The present invention relates to the field of medical instrumentation, specifically to the use of smart technology within miniature remote devices for the inspection, diagnosis, and treatment of internal organs of living organisms. 
     2. Description of Related Technology 
     Endoscopic and colonoscopic techniques are commonly used to inspect the accessible upper and lower portions, respectively, of the human gastrointestinal tract. A traditional endoscopic inspection of a human being (an example of which is the “EGD”) requires the patient to be partially or completely sedated while a long, thin, tubular probe is introduced into the esophagus, routed through the stomach, and ultimately into the upper portion of the small intestine (duodenum). This tubular probe typically contains a self-illuminating fiber optic cable and viewing device to allow visual inspection of tissue in the vicinity of the probe tip. See, for example, U.S. Pat. No. 3,901,220, “Endoscopes” issued Aug. 26. 1975. However, due to the tortuous path, fragility, small diameter, and length of the digestive tract, prior art endoscopic inspection such as the aforementioned EGD is limited to only the stomach and upper portions of the small intestine. See  FIG. 1 . 
     Similarly, traditional colonoscopic examination utilizes a thin, tubular fiber optic probe inserted into the large intestine (colon) via the rectum. Even the most penetrating colonoscopic inspections are limited to the colon and the terminal portion of the small intestine (ileum), due again primarily to the tortuosity and fragility of the large intestine and ileum. While a substantial number of diseases and conditions afflict the stomach. duodenum, colon, and ileum, several others may occur within the remaining, inaccessible portions of the gastrointestinal tract including the jejunum of the small intestine. 
     Both endoscopic and colonoscopic inspections further run a small but significant risk of physical damage to the patient, such as perforation of the duodenum or ileum, especially where disease has progressed to an advanced stage and the surrounding tissue has weakened or degenerated. 
     Alternatively, non-invasive diagnostic techniques such as X-ray inspection (e.g., so-called “upper-GI” and “lower-GI” series), which involves introducing barium or other contrast agents into the patient, are useful in identifying gross abnormalities, but require careful interpretation and are susceptible to misdiagnosis, shielding effects, and a plethora of other potential pitfalls. Furthermore, such techniques expose the patient to significant doses of ionizing X-ray radiation which ultimately may be deleterious to the patients health. 
     The somewhat related technique of X-ray computed axial tomography (CAT) scanning provides information about the general condition of an individual&#39;s intestinal tract and internal organs, yet does not possess the necessary resolution to facilitate diagnosis of many types of conditions. It also suffers from the drawback of exposing the patient to substantial quantities of X-ray radiation. CAT scans of the GI tract also may require the use of ingested and/or intravenous contrast agents, the latter notably having a small but non-zero incidence of patient mortality. Furthermore, certain patients may not be given such contrast agents due to allergies or other pre-existing medical conditions, thereby substantially reducing the efficacy of the CAT scan as a diagnostic technique for these patients. 
     Magnetic resonance imaging (MRI) techniques, well known in the medical diagnostic arts, have certain benefits as compared to the aforementioned CAT scan, yet also suffer from limitations relating to resolution and interpretation of the resulting images, and in certain instances the required use of “contrast” agents. More recently, enhanced MRI techniques are being used to aid in the diagnosis and treatment of Crohn&#39;s disease, yet even these enhanced techniques suffer from limitations relating to resolution, especially when the disease has not progressed to more advanced stages. 
     Another related and well known medical diagnostic technology is that of autofluorescence endoscopy. Simply stated, autofluorescence endoscopy uses a light source having specific characteristics (typically a coherent source such as a laser) to illuminate a portion of tissue under examination; the incident light excites electrons within the atoms of the tissue which ultimately produce a quantum transition therein resulting in an emission of electromagnetic radiation (fluorescence) from the tissue at one or more wavelengths. Additionally, so-called “remitted” energy, which is incident or excitation energy reflected or scattered from the tissue under analysis, is also produced. The fundamental principle behind the autofluorescence technique is that diseased or cancerous tissue has a different autofluorescence (and remitted light) spectrum than that associated with healthy tissue of similar composition; see  FIG. 2 . Generally speaking, diseased tissue autofluoresces to a lesser degree at a given wavelength under the same incident excitation radiation than healthy tissue. See, for example, U.S. Pat. No. 4,981,138, “Endoscopic Fiberoptic Fluorescence Spectrometer” issued Jan. 1, 1991. Unfortunately, however, the applicability of autofluorescence techniques has traditionally been limited to external areas of the body, or those accessible by endoscopic probe, thereby making this technique ineffective for diagnosing diseases of the central portion (jejunum) of the small intestine. See also U.S. Pat. No. 5,827,190, “Endoscope Having an Integrated CCD Sensor”. 
     In summary, endoscopic inspection is arguably the most efficient and effective prior art method of diagnosing conditions of the intestinal tract, especially those of a more chronic and insidious nature. However, due to its limited reach, endoscopic inspection is not an option for diagnosing or treating the central portions of the digestive tract, specifically the central region of the small intestine. 
     Based on the foregoing, it would be highly desirable to provide an apparatus and method by which treatment could be rendered remotely to various portions of the intestinal tract. More specifically, it would be highly desirable to provide an apparatus and method by which visual inspection of all portions of the interior of the digestive tract including the small intestine could be made without invasive surgery or other extraordinary and potentially deleterious means. Furthermore, it would be desirable to provide an apparatus and method by which autofluorescence analysis of the interior of the digestive tract could be performed remotely. 
     SUMMARY OF THE INVENTION 
     The present invention satisfies the aforementioned needs by providing an improved endoscopic device and method of diagnosing and treating patients utilizing the same. 
     In a first aspect of the invention, apparatus for use in the intestinal tract of a living being is disclosed. In a first embodiment, the apparatus comprises: a sensor for collecting data in a first form; a data converter operatively connected to the sensor, the data converter converting the data from the first form to a second form; a digital processor having at least one algorithm running thereon adapted to process at least a portion of the data of the second form; a mass data storage device operatively connected to the digital processor which stores at least a portion of the processed data in the second form; a power supply for powering the sensor, the processor, and the storage device; and a dissolvable covering for at least a portion of the probe. 
     In a second embodiment, the apparatus comprises: means for collecting data in a first form; means operatively connected to the means for collecting, for converting the data from the first form to a second form; processor means having at least one means adapted for processing at least a portion of the data of the second form; means, operatively connected to the processor means, for storing at least a portion of the processed data in the second form; means for powering at least the sensor, the processor, and the means for storing; and means for dissolvably covering at least a portion of the apparatus. 
     In a third embodiment, the apparatus comprises: a sensor for collecting data in a first form; a data converter operatively connected to the sensor, the data converter converting the data from the first form to a second form; a digital processor having at least one algorithm running thereon adapted to process at least a portion of the data of the second form; a data storage device operatively connected to the digital processor which stores at least a portion of the processed data in the second form; a power supply for powering the sensor, the processor, and the storage device; and a housing comprising at least one aperture, the aperture being controlled at least in part by a shutter. 
     In a fourth embodiment, the apparatus comprises: a sensor for collecting data in a first form; data conversion apparatus operatively connected to the sensor, the data conversion apparatus converting the data from the first form to a second form; a digital processor having at least one algorithm funning thereon adapted to process at least a portion of the data of the second form; means for storing operatively connected to the digital processor which stores at least a portion of the processed data in the second form; a power supply for powering the sensor the processor, and the means for storing; and a housing comprising at least one aperture, the aperture being controlled at least in part by a means for selectively occluding the aperture. 
     In a fifth embodiment, the apparatus comprises: a sensor for collecting data in a first form; a data converter operatively connected to the sensor, the data converter converting the data from the first form to a second form; a digital processing device having at least one algorithm running thereon adapted to process at least a portion of the data of the second form; a data storage device operatively connected to the digital processor which stores at least a portion of the processed data in the second form; and a power supply for powering at least the sensor, the processor, and the storage device; at least one light source a fiber-optic bundle adapted to transmit light from the at least one light source to illuminate portions of the intestine. 
     In a sixth embodiment, the apparatus comprises: a sensor for collecting data in a first form; a data converter operatively connected to the sensor, the data processor having at least one algorithm running thereon adapted to process at least a portion of the data of the second form; means, operatively connected to the digital processor, for storing at least a portion of the processed data in the second form; and a power supply for powering at least the sensor, the processor, and the storage device; at least one illuminating means; fiber means for transmitting light from the at least one illuminating means to portions of the intestine. 
     In a seventh embodiment, the apparatus comprises: a sensor for collecting data in a first form, the sensor comprising interleaved visual band and autofluorescence band sensing elements; a data converter operatively connected to the sensor, the data converter converting the data from the first form to a second form; a digital processing device having at least one algorithm running thereon adapted to process at least a portion of the data of the second form; a mass data storage device operatively connected to the digital processor which stores at least a portion of the processed data in the second form; and a power supply for powering the sensor, the processor, and the storage device. 
     In an eighth embodiment, the apparatus comprises: means for collecting data in a first form, the means comprising first means for collecting visual band radiation and second means for collecting autofluorescence band radiation in an interleaved fashion; a data converter operatively connected to the means for collecting, the data converter converting the data from the first form to a second form; a digital processor having at least one algorithm running thereon adapted to process at least a portion of the data of the second form; a mass data storage device operatively connected to the digital processor which stores at least a portion of the processed data in the second form; and a power supply for powering the sensor, the processor and the storage device. 
     In a ninth embodiment, the apparatus comprises: a sensor for collecting data in a first form; data conversion apparatus operatively connected to the sensor, the data conversion apparatus converting the data from the first form to a second form; a digital processing device having at least one algorithm running thereon adapted to process at least a portion of the data of the second form; means for storing operatively connected to the digital processor which stores at least a portion of the processed data in the second form; a power supply for powering at least portions of the apparatus; and a housing comprising at least one aperture, the aperture being controlled at least in part by a means for selectively occluding the aperture. 
     In a tenth embodiment, the apparatus comprises: a sensor for collecting data in a first form; a data converter operatively connected to the sensor, the data converter converting the data from the first form to a second form; a digital processor adapted to process at least a portion of the data of the second form according to at least one algorithm; means, operatively connected to the digital processor, for storing at least a portion of the processed data in the second form; and a power supply for electrically powering at least portions of the probe; at least one illuminating means; fiber means for transmitting light from the at least one illuminating means to portions of the intestine; wherein the probe traverses the at least portion of the intestine due to the peristaltic action thereof. 
     In an eleventh embodiment, the apparatus comprises: a sensor for collecting data in a first form; a data converter operatively connected to the sensor, the data converter converting the data from the first form to a second form; a digital processing device adapted to process at least a portion of the data of the second form according to at least one algorithm; a data storage device in data communication with the digital processor which stores at least a portion of the processed data in the second form a power supply providing electrical power to at least portions of the apparatus; and a dissolvable covering disposed on at least a portion of the probe. 
    
    
     
       BRIEF DESCRIPTION OF THE DRAWINGS 
         FIG. 1  is a representation of the human digestive tract, illustrating the locations and typical extent of prior art endoscopic and colonoscopic inspection techniques. 
         FIG. 2  is a typical autofluorescence spectrum of intestinal tissue illustrating the difference in response for normal and diseased tissue based on exposure to light at a wavelength in the range of 450 to 700 nm. 
         FIG. 3  is a perspective view of a first embodiment of the smart probe of the present invention. 
         FIG. 4  is a front view of the smart probe of  FIG. 3  illustrating the arrangement of the lenses and the CCD array. 
         FIG. 5  is a cross-sectional view of the smart probe of  FIG. 3  taken along line  5 — 5 , showing the internal arrangement of components therein. 
         FIG. 5   a  is a cross-sectional view of the smart probe of  FIG. 3  taken along line  5   a — 5   a , further showing the internal arrangement of components therein. 
         FIG. 6  is a block diagram of one preferred embodiment of the data acquisition, processing, storage, and transfer circuitry of the smart probe of  FIG. 3 . 
         FIG. 7  is a block diagram of one preferred embodiment of an inductive power transfer circuit used in the smart probe of  FIG. 3 . 
         FIG. 8  is a perspective view of one embodiment of the MCD and its associated remote unit according to the present invention. 
         FIG. 9  is a block diagram illustrating the data processing and power transfer components of the MCD and its associated remote unit. 
         FIGS. 10   a  and  10   b  are perspective and front views, respectively, of a second embodiment of the smart probe of the present invention. 
         FIG. 11  is a cross-sectional view of the smart probe of  FIG. 10   a,  taken along line  11 — 11 . 
         FIG. 12  is a block diagram of one preferred embodiment of the data acquisition, processing, storage, and transfer circuitry of the smart probe of  FIG. 10 . 
         FIG. 13   a  is a cross-sectional view of a first embodiment of an improved endoscopic delivery device capable of implanting the smart probe of the present invention within the intestinal tract of a patient. 
         FIG. 13   b  is a elevated plan view of the closure of the delivery device of  FIG. 13   a.    
         FIG. 14  is a cross-sectional view of second embodiment of an improved endoscopic delivery device capable of implanting the smart probe of the present invention within the intestinal tract of a patient. 
         FIG. 15  is flow diagram illustrating one embodiment of the method of diagnosing and/or treating the intestinal tract of a patient using the smart probe of the present invention. 
     
    
    
     DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS 
     Reference is now made to the drawings wherein like numerals refer to like parts throughout. 
     As used herein, the term “autonomously” shall mean independent of direct physical or tactile control by an operator or external device. As will be described in greater detail below, the smart probe of the present invention is designed to be initially introduced into the patient after which time the probe operates autonomously; i.e., only utilizing electrical, inductive, magnetic, or radio frequency signals to enable or perform certain desired functions, with no direct external physical contact or connections. This is to be distinguished from prior art endoscopic inspection or treatment devices, which always maintain some physical or tactile link (such a tube, electrical wire, or fiber optic bundle) with the operator, and hence which do not operate autonomously while in the patient. 
       FIG. 3  is a perspective view of a first embodiment of the smart probe of the present invention. The probe  300  comprises an outer housing  302  having a generally ellipsoid shape and an inner cavity  303  (not shown), a lens aperture  304  positioned in one end of the housing  302 , and lenses  306   a,    306   b  mounted in alignment with the aperture  304  within a lens retaining board  305 . An optional lens cover  308  covers the lenses  306   a ,  306   b  and seals the aperture  304 . A plurality of other components (including, inter alia, a CCD array, microcontroller, clock, parallel/serial drivers, and sample and hold circuitry, not shown) are disposed within the aforementioned cavity  303  or otherwise within the outer housing  302  itself. These other components are described in greater detail below with reference to  FIGS. 6–7 . A generally ellipsoid shape is used for the outer housing  302  of the present embodiment to facilitate passage of the probe  300  through the intestinal tract of the patient, and to assist in maintaining the proper orientation of the probe during use; e.g., such that the lenses  306  are oriented to have sufficient perspective and focal length to adequately view portions of the interior of the patient&#39;s intestine. Optionally, the rear portion of the probe  300  may be flared, or other contours or devices utilized to assist in orientation within the intestine. While the present embodiment utilizes a generally ellipsoid shape for the outer housing  302 , it will be recognized that other shapes and configurations for the outer housing (and lens aperture  304 ) may be used in accordance with the present invention. For example, substantially cylindrical or “bullet-shaped” outer housings could be used. Alternatively, an outer housing having a non-symmetric lateral cross-section (i.e., that taken in a plane to which the longitudinal axis of the housing  302  is normal) could be employed. Many other suitable shapes exist. 
     Furthermore, it will be recognized that the probe  300  may operate in both a “forward looking” and “rearward looking” orientation within the patient. Specifically, the probe may be disposed within the intestine such that the aperture  304  (and associated CCD array) is oriented in the direction of probe advance, or alternatively rearward. As described in more detail below, it is further contemplated by the present invention that the probe may be equipped with both forward and rearward looking CCD arrays. 
     The outer housing  302  is sized in the present embodiment to have a diameter (at its widest point, measured across its circumference) on the order of 12 mm (roughly 0.5 in.) in order to allow unencumbered passage through the intestinal tract and even the ileocecal valve. However, it will be appreciated that other sizes of probe, both smaller and larger, may be used depending on a variety of factors including the size of, and any peculiarities associated with, a given patient&#39;s intestines, as well as the instrumentation/components desired to be carried by the probe  300 . 
     The outer housing  302  is in the present embodiment constructed of a mechanically rigid and stable polymer such as ethylene tetrafluoroethylene (Tefzel®) which is also resistant to chemical exposure and other environmental influences, and which is also nontoxic to the patient. Tefzel® also has the desirable property of being able to be fabricated with a smooth (i.e., low coefficient of friction) surface which further facilitates passage of the probe  300  through the intestinal tract, although this property is not essential. It can be appreciated, however, that other materials (such as certain metals, resins, composites, or even organic materials) may be used to form all or part of the outer housing  302 . For example, the housing need not be a discrete component, but rather may be an encapsulant such as that used on integrated circuit devices. 
     The housing  302  is made of minimal wall thickness so as to have adequate rigidity yet permit the maximum size cavity therein. In the present embodiment, a wall thickness of 0.5 mm (roughly 0.020 in.) is selected, although other values may be used. The outer housing of the probe of  FIG. 3  is split circumferentially at the mid-section to facilitate component insertion and removal. The halves of the housing  302   a,    302   b  are fit tightly together so as to minimize the possibility of fluid leaking into the cavity  303 . A sealing agent  580  (and/or a sealing ring or gasket) is used to further prevent fluid leakage. Note also that such sealing is applied around the interface of the lens board  305  and the outer housing  302 , as shown in  FIG. 5 . 
     One or more data transfer terminals  532  and power transfer terminals  716  are embedded at or near the surface of the probe housing  302  to facilitate data and power transfer, respectively, between the probe  300  and the MCD  800  ( FIG. 8 ). In the present embodiment, the terminals  532 ,  716  are ring-shaped so as to permit data/power transfer in any rotational orientation of the probe  300  around its longitudinal axis; however, it will be recognized that other terminal shapes and configurations may be used. 
     The lens cover  308  shown in  FIG. 3  is designed to protect the lenses  306   a,    306   b ,  306   c  from becoming occluded by substances present in the intestine of the patient during probe travel. Ideally, the patient will be restricted from eating or ingesting any substance for a suitable period prior to probe use so as to minimize any such occlusions; however, the lens cover  308  further assists in maintaining the lenses clear prior to use. The lens cover  308  of the present embodiment is a thin membrane (on the order of a few thousandths of an inch thick) and is comprised of a substantially clear gelatin-like substance comparable to that commonly used to contain and deliver pharmaceutical products (such as so-called “gel caps” which are well known in the pharmaceutical arts) or equivalent thereof. The design and composition of the lens gel substance is, in the present embodiment, controlled so as to provide a timed dissolution within the patient. For example, if it is estimated that the intestinal motility of the patient is X cm/hr, and the region of the intestine desired to be inspected using the probe  300  is Y cm from the point of introduction of the probe, then the lens cover  308  can be chosen to dissolve in roughly Y/X hr or less (allowing for some margin of error). The lens cover  308  of the present embodiment is shaped to conform roughly with the outer surface of the lens(es)  306  and with the profile of the outer housing  302  such that the cover  308  is maintained within the housing aperture  304 , and provides minimal optical distortion, until it dissolves. Note also that a substantially clear material is chosen to permit the passage of some light through the cover  308  before its dissolution, although lens covers with other optical properties (such as selective wavelength filtration) may be used. 
     It should be noted that while the present embodiment makes use of a lens cover  308 , the use of such cover may not be necessary in certain applications, and therefore need not be present. Furthermore, while the present embodiment describes a lens cover which is chemically dissolvable, other types of lens covers may be employed with the present invention. For example, a mechanical shutter arrangement could be used to selectively cover/uncover the lenses  306 . Alternatively, a lens cover which dissolves or otherwise alters its properties when exposed to an electrical current or coherent electromagnetic radiation may be employed. A permanent (i.e., non-dissolving) lens cover having desirable optical properties could also be used. 
     Referring now to  FIG. 4 , a front view of the smart probe  300  of  FIG. 3  is shown, illustrating the relationship of the housing aperture  304 , lenses  306 , the CCD array  402 , and the lens cover  308 . Specifically, the aperture  304  is sized and shaped to permit light of varying wavelengths to impinge upon the active region  404  of the CCD array  402 , and to accommodate the optical light lens  306   b  which is positioned laterally to the main lens  306   a  in this embodiment. The aforementioned lens cover  308  generally conforms to the outer surface of each of the lenses  306   a,    306   b,  thereby acting as a protective cover for each before dissolution. As will be described in greater detail herein, the optical lens  306   b  acts to transfer and distribute broad spectrum visible light generated within the probe  300  to intestinal tissue in proximity to the lenses. Remitted or reflected visible is passed through the main lens  306   a  (which is chosen to be effectively transparent to a broad range of wavelengths in the spectral regions of interest) to the CCD array  402 . The main lens  306  is, in the embodiment of  FIGS. 3 and 4 , a substantially convex lens designed to gather and more narrowly focus energy originating from various positions outside the probe  300  onto the CCD array  402 . The optical lens  306   b  is, conversely, designed to radiate and distribute light incident on its inner surfaces (via the associated fiber optic bundle, described below) more broadly within the intestine. 
     The CCD array  402  of the present embodiment is a multi-pixel semi-conductive device having anti-blooming protection, and being sensitive to various wavelengths of electromagnetic radiation. A Texas Instruments Model TC210 192×165 pixel CCD image sensor is chosen for use in the present embodiment, based on its performance attributes, spectral responsivity, and size (i.e., the package outline is roughly 5 mm by 3 mm), although myriad other devices could be used with equal success. The operation of the CCD array  402  is described in greater detail below. 
     Referring now to  FIGS. 5 and 5   a,  cross-sections of the probe  300  of  FIGS. 3 and 4  are illustrated. The probe outer housing  302  generally contains a number of different components in its internal cavity  303  including the aforementioned lenses  306  and CCD array  402 , as well as a light emitting diode (LED)  504 , a single mode fiber optic bundle  506 , and one or more inductive data transfer terminals  532 . A number of discrete or integrated semiconductor components are also present within the probe  300 , including a “flash” analog-to-digital converter ADC  512 , sample and hold circuit  514 , parallel and serial drivers  516 ,  518 , microcontroller (or microprocessor)  520 , clock driver  524 , and a data interface circuit  526  as described in greater detail below. The LED  504  is located roughly co-linearly with the central axis of its lens  306   b  with the fiber optic bundle  508  disposed there between as shown in  FIG. 5 . The LED  504 , its fiber optic bundle  508 , and its lens  306   b  are optically coupled so as to transmit light energy to the lens in an efficient manner. The A/D converter  512 , drivers  516 ,  518 , microcontroller  520 , and other electronic components are disposed within the cavity  303  on one or more miniature printed circuit board assemblies (PCBAs)  510  in a space-efficient manner, with the semiconductor components being disposed and electrically connected on either side of the assemblies  510 . The semiconductor packages are chosen so as to fit within the housing, as discussed in more detail herein. One or more inductive data transfer terminals  532  generally in the form of circumferential rings are disposed within the outer housing at or near the surface thereof as previously described in order to provide for data transfer between the probe  300  and the remote unit  802  of the MCD data processing and analysis equipment  800  external to the patient (see discussion of  FIG. 8  below). Additionally, one or more inductive power transfer terminals  716  are positioned on the outer portion of the housing to facilitate inductive power transfer between the MCD and the probe  300 . Inductive power transfer is chosen in the present embodiment so as to obviate the need for a chemical battery or other potentially hazardous power source within the probe  300 , although a battery may be used. Alternatively, in another embodiment, a radio frequency (RF) oscillator and supporting circuitry (not shown) is disposed within the housing  302  on the PCBA  510  to receive radio frequency energy generated externally to the patient and convert this energy to direct current power within the probe  300 . 
     So as to fit within the limited volume of the cavity  303 , each of the aforementioned components  504 ,  510 ,  512 ,  514 ,  516 ,  518 ,  520 ,  524 ,  526  is chosen to have the minimum physical profile. While several discrete component functions are depicted in the functional block diagram of the probe data acquisition and transfer circuitry  600  (described below with reference to  FIG. 6 ), in actuality many of these functions can be integrated and performed by a lesser number of devices so as to economize on space. For example, a Texas Instruments MSP430×MSP ultra low power microcontroller (such as in the “DW package”) incorporating internal memory, clock, and ADC may be used in the resent embodiment. Application specific integrated circuits (ASICs), FPGAs, or other custom ICs having a high degree of integration may also be used for such purposes. Such integration is desirable in the present invention, and is presently well within the capability of those skilled in the semiconductor design and fabrication arts. Alternatively, a larger number of discrete components (as shown in  FIG. 5 ) may be used. For example, a Texas Instruments TLV2543C flash ADC with a 20 pin “DB” package (roughly 8 mm×7.5 mm×2 mm) may be used as the ADC  512  of the present embodiment. This package more than adequately fits within the aforementioned 12 mm outer housing  302  (assuming a 0.5 mm housing wall width), while preserving space for the other components. Preferably, a BGA (ball grid array) package is utilized to eliminate leads along the edge of the package(s) and further economize on space. It will be appreciated, however, that a wide variety of integration schemes, packages, profiles, and lead (pin) structures may be used in the present invention in order to simultaneously fit all of the desired components within the aforementioned outer housing  302 . 
     The circuit board assemblies  510  of the present embodiment are preferably multilayer boards having a plurality of circuit traces, vias, and contact pads disposed therein to facilitate electrical interconnection of the various terminals of the integrated circuits (ICs) and any discrete electrical components (such as the LED  504 , resistors, capacitors, or transistors). The design and fabrication of such circuit boards is well known in the electrical arts. Electrical interconnection between the multiple PCBAs  510  of  FIG. 5  is accomplished via miniature flexible electrical tracing (not shown). Note that in the present embodiment, the PCBAs  510  are disposed in a generally longitudinal fashion (i.e., parallel to the longitudinal axis of the probe housing  302 ); however, other orientations, such as transverse to the longitudinal axis, could be used. 
     The LED  504  used in the embodiment of  FIGS. 3–5  is a standard, low voltage light-emitting diode having a spectral emission characteristic centered in the visible wavelengths. In the present embodiment, a “white light” LED of the type well known in the electrical arts is preferred, although other types, power ratings, and spectral outputs are possible. This LED  504  is used as an optical illumination source for the CCD array  402  previously described. Specifically, light generated by the LED is passed via its fiber optic bundle  508  to the optical lens  306   c  and radiated out of the probe  300  into the region immediately surrounding the CCD array  402 . The fiber optic bundle is, in this embodiment, a single mode optical fiber of the type well known in the optical transmission arts. Light reflected by the interior surfaces of the patient&#39;s intestine is gathered by the main lens  306   a  and focused on the CCD array  402 , including the visual sub-array  402   b,  where it generates charge within the individual CCD array cells. The voltage and power rating of the LED  504  is chosen to be compatible with the desired light intensity, power supply circuit capacity, and system voltage available within the probe. In the present embodiment, a milliwatt LED is used having a voltage rating on the order of 2–5 Vdc, although other may be used. 
     Referring now to  FIG. 6 , one embodiment of the data acquisition, processing, and transfer circuit  600  of the smart probe of  FIGS. 3–5  is disclosed. As previously described, the circuit  600  of the present embodiment comprises a number of components including, inter alia, a CCD array  402 , parallel and serial drivers  516 ,  518 , sample and hold circuit (SHC)  514 , system clock  524 , microcontroller  520 , amplifier  522 , ADC  512 , and data transfer sub-circuit  526 . Other electronic elements (such as capacitors, resistors, transistors, and diodes; not shown) are also used to facilitate operation of the circuit  600 ; the use of such components is well known in the relevant arts and accordingly will not be discussed further herein. Furthermore, it will be noted that such electronic elements are ideally integrated with one or more of the aforementioned components  512 ,  514 ,  516 ,  518 ,  520 ,  522 ,  524 ,  526  in order to minimize space consumed within the probe outer housing  302 . 
     As shown in  FIG. 6 , the CCD array is driven by the parallel and serial drivers  516 ,  518  based on a user-defined clock signal output from the clock/timer  524  and controlled by the microcontroller  520 . Analog signals output from the CCD array are amplified by amplifier  522  and passed to SHC  514 . Analog signals output from the SHC  514  are rapidly converted by the ADC  512  into digital signals, the latter being input to the data transfer sub-circuit  526 . A “flash” ADC (i.e., one with a sampling rate on the order of microseconds or less) is used to permit streaming of video data at video rates, typically 7–20 MHz. A 10 or 12-bit resolution ADC may be used, for example, to accommodate the dynamic range of the CCD. The required ADC resolution can generally be determined by the following relationship:
 
N≧(DR/6.02)
 
Where:
         N=Number of data bits   DR=Dynamic Range of CCD in db
 
The data transfer sub-circuit  526  comprises a modulator  528 , demodulator/filter  529 , transistor stage  530 , and data transfer terminal  532 . The construction and operation of inductive terminals is well known in the electronic arts, and is described in, inter alia, U.S. Pat. No. 4,692,604 “Flexible Inductor” issued Sep. 8, 1987, which is incorporated herein by reference in its entirety. Note that in the present embodiment, the “flexible” inductor of the &#39;604 patent is configured so as to form a circumferential ring within the probe outer housing, as shown in  FIG. 3 . A high frequency (MHz) clock signal is supplied by the clock  524  to the modulator  528  so as to generate an ac carrier. The data signal output from the ADC  512  is used by the modulator  528  to modulate the aforementioned ac carrier, thereby producing an amplitude modulated ac waveform on the coil of the data terminal  532  by way of the transistor stage  530 . The output of the probe data terminal  532  is a magnetic flux which varies according to the amplitude modulated ac signal carried on the terminal coil. The coil  542  of the MCD remote unit data terminal  540  is inductively coupled to the probe data terminal coil via the magnetic flux; accordingly, an amplitude modulated, alternating current signal of the same phase and frequency is generated in the remote unit coil  542 . This signal is then demodulated using, for example, a diode and filter capacitor as described in U.S. Pat. No. 4,605,844, “Computerized Transaction Card With Inductive Data Transfer”, issued Aug. 12, 1986, which is also incorporated by reference herein in its entirety. The resulting demodulated data signal, a replica of the data signal supplied by the output of the ADC  512 , is input to the front-end processing (e.g., DAC or DSP) of the MCD, as described with reference to  FIGS. 8 and 9  below. It will be further recognized that the design of the data transfer sub-circuit  526  must consider the video data rates previously described (typically 7–20 MHz).
       

     The demodulator/filter  529  performs two functions: (i) demodulating the control and data signals sent by the MCD microprocessor during probe startup and operation; and (ii) isolation and filtering of any errant power transfer signal which couples to the inductive coil(s) of the data transfer terminal  532 . 
     Referring now to  FIG. 7 , one embodiment of the inductive power transfer circuit  700  used in the smart probe of  FIGS. 3–6  and MCD remote unit  802  is described. Similar to the inductive data transfer sub-circuit  526  illustrated in  FIG. 6 , the power transfer circuit  700  utilizes a clocking signal generated by the clock  702  in the MCD remote unit  802  to supply a parallel transistor stage  703  including two pairs of transistors  704   a,    704   b  and associated MOSFETs  706   a,    706   b . One pair of transistors  704   a  is supplied via an signal inverter  708  so as to invert the phase (i.e., shift by 180 degrees) of the signal with respect to the non-inverted signal supplied to transistors  704   b.  An alternating current waveform (of a different frequency than that imposed upon the data transfer terminal(s)  532 ) is accordingly generated within the coil  710  of power transfer terminal  712 , which is inductively coupled to the coil  714  of the power transfer terminal(s)  716  in the probe  300 . A diode (rectifier) stage  720  including filter capacitor (not shown) is used to convert the induced ac signal in the probe coil  714  to direct current. A voltage regulator and conversion circuit  722  is used to regulate and adjust the voltage of the converted dc power prior to supply to the other components  402 ,  504 ,  512 ,  514 ,  516 ,  518 ,  520 ,  522 ,  524 , and  526  within the probe  300  via the various voltage busses  730 ,  732 ,  734 . The construction and operation of voltage regulating and conversion circuits is well known in the electrical arts, and will not be discussed further herein. U.S. Pat. No. 4,692,604, previously cited herein, describes the construction and operation of inductive power transfer circuits such as that utilized herein in greater detail. 
     Similarly, it will be noted that the method of clocking signal recovery described in the above-referenced patent may be utilized in the present invention to obviate the clock  524  of  FIG. 6 . Specifically, the ac waveform transferred from the MCD remote unit  802  can be used to generate a clock signal prior to rectification by the diode stage  720  using a clock recovery circuit  740 . This clock signal may then be used to drive those components requiring a clock signal, such as the CCD array  402 , ADC  512 , etc. 
     It will be further recognized that while the present embodiment utilizes inductive data and power transfer, other methods of such transfer are possible. See, for example, the capacitive data transfer apparatus described in U.S. Pat. No. 4,816,654, “Improved Security System for a Portable Data Carrier”, issued Mar. 28, 1989, which is incorporated herein by reference in its entirety. 
     Referring now to  FIG. 8 , the monitoring and control device (MCD)  800  of the present invention includes, in a first embodiment, a remote unit  802  which can be placed in close proximity to the patient&#39;s abdomen in the region of the intestine where the probe  300  is located to permit inductive data and power coupling thereto. The remote unit  802  includes, inter alia, one or more inductive data terminals  540 , and one or more inductive power transfer terminals  712  These terminals  540 ,  712  are located within the unit so as to provide adequate separation during operation, yet still permit simultaneous contact with the probe  300  while in the patient. The operation of these terminals is described in greater detail above with respect to  FIGS. 6 and 7 . As shown in  FIG. 8 , a circular “ring” configuration is used for the terminals  540 ,  712  in the present embodiment so as to minimize the effects of different azimuthal orientations of the remote unit  802  with respect to the probe  300 , although it will be appreciated that other configurations (such as pins, rods, strips, etc. may conceivably be used). As the probe  300  slowly moves within the intestine, the remote unit  802  is moved accordingly by the operator so as to maintain contact therewith. Since the inductive coupling between the data and power transfer terminals  540 ,  712  of the remote unit and terminals  532 ,  716  of the probe is substantially affected by the distance between the respective terminals, as well as the interposed material (tissue, fluids, etc.), the remote unit  802  must be periodically moved while the probe  300  is in use. 
     The remote unit is connected to the MCD main unit  804  via a standard data transmission cable  806  of the type well known in the electrical arts. As further illustrated in  FIG. 9 , the MCD main unit  804  of the present embodiment includes, inter alia, a “flash” digital to analog converter (DAC)  902 , digital signal processor (DSP)  904 , microprocessor  906 , encoder  908 , video display driver  910 , display unit  912 , video memory  914 , and nonvolatile storage device  916 . Image data transmitted from the probe  300  is passed to the main unit  804  from the remote unit  802 , de-compressed if required by the DSP  904 , converted to an analog format by the DAC  902 , coded by the video encoder  908 , and displayed on the display unit  912 . These displayed visual or autofluorescence images constitute one form of diagnostic aid according to the present invention, although it will be recognized that other such aids (such as ultrasound images) may be produced. Images may be stored in the storage device  916  for a variety of functions (such as later retrieval or enhancement) if desired, as is well known in the electronic arts. The microprocessor  906  acts to control the operation of the MCD  804  as well as the probe  300  via data signals transmitted to the probe during startup and operation. Specifically, the microprocessor  906  of the MCD generates and passes control data to the microcontroller  520  of the probe via a modulator circuit  911  and the inductive data terminals  532 ,  540  on startup to initiate microcontroller control of the probe. The probe microcontroller  520 , which is connected to and receives input from the clock  524  (or alternatively, the clock recovery circuit  740  associated with the power transfer circuitry), switches power to the remaining (non-powered) probe components such as the SHC  514  and ADC  512  and generates the necessary signals to the various probe components (based on its internal programming) so as to initiate operation of the LED  504 , collection of image data via the CCD array  402 , and subsequent processing/transfer of the collected data. 
     The remote unit  802  of the MCD  800  is, in a second embodiment, a band which is fitted around the abdomen of the patient (not shown). This band includes a plurality of individual data and power transfer terminals each of which are capable of transferring data and power inductively between the MCD and the probe  300 . The terminals are physically arranged in an interleaved fashion (alternating data and power transfer terminals) so as to provide a high density of terminals yet minimize any interference between terminals. The data terminals are electrically arranged so as to allow the MCD to select and display data received from one or more of the data terminals (channels). This multi-terminal approach is used to allow the probe to maintain contact with the MCD remote unit with minimal or no movement of the remote unit. As the coupling between one set of data terminals is increased with respect to the other terminals, the signal quality for that channel increases accordingly. In one embodiment, the digital data received from the data terminals is input to a high frequency multiplexer. The multiplexer generates a single multiplexed output (based on the multiple data channel inputs) which is input to a DSP. The DSP samples and analyzes the data on the single multiplexed channel for each input channel using an internal algorithm to evaluate the strength and quality of signal on that input channel. The microprocessor selects the most viable channels at any given time based on the output of the signal sampling algorithm running on the DSP, and utilizes the selected input channel as the data source for the DAC and video driver. 
     Conversely, all of the multiple power transfer terminals in the remote unit of the second embodiment are driven synchronously and simultaneously by the MCD so as to permit inductive coupling with the probe at all times, thereby minimizing power “drop outs”. 
       FIG. 10   a  is a perspective view of a second embodiment of the smart probe of the present invention. The probe  1000  of  FIG. 10   a  comprises an outer housing  1002  having a generally cylindrical shape with rounded ends (“capsule”), an inner cavity  1003  (not shown), and a lens aperture  1004  positioned in one end of the housing  1002 . Three lenses  1006   a,    1006   b,    1006   c  are mounted in alignment with the aperture  1004 , and optionally protected by a lens cover. The third lens  1006   c  of the present embodiment is used to distribute laser (coherent) light energy generated by a laser diode which is described in greater detail below. The CCD array  1010  includes two sub-arrays  1010   a,    1010   b  ( FIG. 10   b ) for the collection of visible ambient and light emitted by autofluorescence, respectively. The probe  1000  further includes a digital signal processor (DSP) and memory (not shown) which facilitate processing and storage of the data collected by the CCD sensor and control of the probe, as described below. Data transfer terminals  1040  and power transfer terminals  1043  are embedded at or near the surface of the housing  1002 , as in previous embodiments. 
     Referring now to  FIG. 10   b,  a front view of the smart probe  1000  of  FIG. 10   a  is shown, illustrating the relationship of the housing aperture  1004 , lenses  1006 , the CCD array  1010 , and the lens cover  1008 . Specifically, the aperture  1004  is sized and shaped to accommodate the CCD array  1010  and associated main lens  1006   a,  laser energy lens  1006   b,  and the optical light lens  1006   c.  The laser and optical lenses  1006   b,    1006   c  are positioned laterally to the main lens  1006   a  in this embodiment. The aforementioned optional lens cover  1008  conforms to the outer surface of each of the lenses  1006   a,    1006   b ,  1006   c.  Both remitted visible light and emissions resulting from the autofluorescence of the surrounding tissue are passed through the main lens  1006   a  (which is chosen to be effectively transparent to a broad range of wavelengths in the spectral regions of interest) to the CCD array  1010 . The main lens  1006   a  is, in the embodiment of  FIGS. 10   a  and  10   b,  a substantially convex lens designed to gather and more narrowly focus energy originating from various positions outside the probe  1000  onto the CCD array  1010 . The laser lens  1006   b  and optical lens  1006   c  are, conversely, designed to radiate and distribute light incident on their inner surfaces (via their associated fiber optic bundles) more broadly within the intestine. 
     The CCD array  1010  of the present utilizes an interleaved design whereby individual charge collecting cells having sensitivity to broad spectrum visible light are spatially mixed with cells having sensitivity within a range of wavelengths ideally centered on the autofluorescence peak associated with biological tissue within the interior of the patient&#39;s intestine (530 nm in the present embodiment). Hence, two separate CCD sub-arrays are formed (each having approximately half of the total number of cells in the array  1010 ); (i) a “visible” light sub-array  1010   a,  and (ii) an “autofluorescence” sub-array  1010   b.  As shown in  FIG. 10   b,  the pixels of the two sub-arrays  1010   a,    1010   b  are physically interleaved such that alternation between the pixels of each sub-array occurs in the row dimension only. Therefore, when reading voltage data out of the array  1010  on a row-by-row basis, data from successive cells will be associated with alternating sub-arrays. When data is serially read out of the array  1010  of  FIG. 10   b  in the column direction, an entire column is associated with the same sub-array. This arrangement is used to permit the data acquisition circuitry (described further below with respect to  FIG. 12 ) to readily parse data from the two sub-arrays  1010   a,    1010   b  and store it at different locations within the device memory  1026 . It will be recognized that other types of interleaving of the array  1010  may be used in conjunction with the present invention, however. For example, alternation of pixels on a column basis may be used. Alternatively, pixels could be alternated on both a row and column basis. Furthermore, interleaving of the pixels need not be used; rather, a single multifunction CCD array, or a system of two or more discrete CCD arrays arranged in some other spatial relationship (such as side-by-side, or over-under) could be used, either with a single lens  1006   a  as shown in  FIG. 10   b,  or separate, dedicated lenses. 
     Referring now to  FIG. 11 , a cross-section of the probe  1000  of  FIGS. 10   a  and  10   b  is illustrated. The probe outer housing  1002  generally contains a number of different components in its internal cavity  1003  including the aforementioned lenses  1006   a,    1006   b ,  1006   c  and CCD array  1010 , as well as a semiconductor laser  1012 , light emitting diode (LED)  1014 , two respective single mode fiber optic bundles  1016 ,  1018 , and one or more data transfer terminals  1020 . A number of discrete or integrated semiconductor components are also present within the probe  1000 , including, inter alia, an analog-to-digital converter (ADC)  1022 , a digital processor  1024 , microcontroller  1025 , digital memory  1026  with integral memory controller, as described in greater detail below. The semiconductor laser  1012  and LED  1014  are located approximately co-linearly with the central axis of their respective lenses  1006   b,    1006   c,  with the fiber optic bundles  1016 ,  1018  disposed there between as shown in  FIG. 11 . The laser and LED  1012 ,  1014 , their respective bundles  1016 ,  1018 , and respective lenses  1006   b,    1006   c  are optically coupled so as to transmit light energy to the lenses in an efficient manner. The ADC  1022 , signal processor  1024 , memory  1026 , and other electronic components are disposed within the cavity  1003  on one or more miniature printed circuit board assemblies (PCBAs)  1030  in a space-efficient manner, with the semiconductor components being disposed and electrically connected on either side of the assemblies  1030 . One or more data transfer terminals  1040  in the form of circumferential rings are located within the outer housing at or near the surface thereof in order to provide for data transfer between the probe  1000  and the MCD remote unit (not shown). Additionally, a power transfer circuit  1042  with transfer terminals  1043  similar to that described with respect to the embodiment of  FIGS. 3–7  is disposed within the housing  1002  on a PCBA  1030  to receive and demodulate inductive modulated energy generated externally to the patient by the MCD remote unit. Optionally, in yet another embodiment, a NiMH or comparable miniature battery (not shown) and supporting circuitry may be included within the outer housing  1002  as a power source in lieu of the aforementioned inductive power circuit  1042 . 
     As previously discussed with respect to the embodiment of  FIGS. 3–7 , the package profiles of the components used within the present embodiment are chosen so as to permit all of the above-described components to be fit within the outer housing. This becomes particularly critical with respect to the embodiment of  FIGS. 10   a,    10   b,  and  11 , since there are substantially more components contained within the outer housing  802 . The size of each component package must be weighed against the necessity of the component and the overall available space within the probe housing  1002 . For example, when choosing a DSP package, the necessary MIPS, degree of integration of other functions within the DSP (such as, DMA, internal memory, etc.) are balanced with the available space within the housing. Similarly, the memory storage capacity is balanced with the physical package size in order to optimize all parameters. Also, as previously discussed, the use of highly integrated multifunction devices is desirable in order to reduce the size of the probe  1000 . For example, embedded memory (i.e., that integrated within the DSP or other component package) may be employed as the capability of such devices increases. Furthermore, the placement of the individual components at various locations on the PCBAs  1030  (as well as the placement of the PCBAs themselves) is optimized for space. 
     In light of the foregoing, it will be appreciated that the size and shape of the probe outer housing  1002  can be adjusted to accommodate internal components of varying sizes, consistent with the requirement that the housing be sized and shaped to permit passage through the desired portion of the patient&#39;s intestinal tract. Typically, the ileocecal valve at the juncture of the small and large intestines will constrain the maximum diameter of the probe housing. The probe housing  1002  of the embodiment of  FIGS. 10–11  is larger (roughly 40 mm in length, and 15 mm in diameter) than that of the embodiment of  FIGS. 3–5  (roughly 30 mm in length, and 12 mm in diameter), although it will be recognized that other sizes and shapes may be used. 
     The laser  1012  of the smart probe  1000  is now described. A semiconductor (diode) laser is used in the embodiment of  FIGS. 10–11  to generate laser energy in the desired wavelength band. In the present embodiment, a center wavelength of 530 nm (corresponding to green light) is used, although it will be recognized that other wavelengths may be chosen based on the response of certain types of tissue and the needs of a specific application. As shown in  FIG. 2 , the ratio of measured fluorescent intensity for diseased tissue to that of normal tissue is minimized (and both the absolute intensity and intensity difference maximized) at roughly 530 nm, thereby effectively increasing the resolution and signal-to-noise ratio of the system without additional processing. A micro-package diode laser is utilized based on availability and cost, output power, size, and power consumption considerations, although other lasers may be used. A laser driver circuit  1013  (such as a model NS102 manufactured by NVG Corporation) is used in conjunction with the aforementioned laser diode in order to control the operation and output of the diode. Note that the size of the laser diode and driver circuit (on the order of a few millimeters in all dimensions) allows conservation of space within the probe outer housing  1002 . The laser  1012  may be configured to operate in either pulsed or CW (continuous wave) modes, or both, depending on the needs of the operator. Switching between modes of operation is accomplished via the microcontroller  1025 , as is well known in the art. 
     Referring now to  FIG. 12 , one embodiment of the data acquisition, storage, and transfer circuit  1200  of the present invention is described. As shown in  FIG. 12 , the circuit  1200  comprises generally a combined CCD array  1010 , analog-to-digital converter (ADC) 1022 , digital signal processor (DSP) 1029 , microcontroller  1025 , random access memory (RAM) with integral memory controller  1026 , and a data transfer sub-circuit  1027 . Other components include a system clock/timer  1044 , parallel/serial drivers  1046 ,  1048 , sample and hold circuit  1050 , data compression algorithm (running on the DSP), and data transfer terminal(s)  1040 . The function and operation of these components are described in greater detail below. 
     As previously described, the CCD array  1010  is used to gather light energy of varying wavelengths, and produces a voltage output which is proportional to the intensity of the incident light. Note that during laser operation, the cells of the CCD may be drained if required to prevent damage. The analog output of the CCD array is fed to the ADC  1022 , which converts the analog signal to a digital representation. The ADC of the present embodiment has at least two analog input channels which are multiplexed to permit the conversion of analog voltage data generated by either of the CCD sub-arrays  1010   a ,  1010   b to a digital format. The digital output of the ADC is fed to the DSP  1024  which performs a variety of control and signal processing functions including demultiplexing of the multiplexed ADC signals, and signal compression for storage in the memory  1026 . The DSP takes the digital data received from the ADC, demultiplexes and formats it, and optionally compresses it for storage within the memory using any number of data compression techniques such as pulse code modulation (PCM) or delta pulse code modulation (DPCM), which are well known in the signal processing arts. Data compression is performed within the DSP using an algorithm adapted for such purpose which is stored within the program or flash memory of the DSP  1024  or, alternatively, within the off-chip memory  1026 . It will be appreciated that while a DSP having a program memory is used in the present application, other types of processors may be substituted based on the chosen data acquisition and transfer properties. A discretely packaged DSP such as a Texas Instruments TMS320C2xx series processor (roughly 14 mm×14 mm×2 mm in the “PN” PQFP package) could feasibly be used in the present embodiment, although as previously discussed, it is desirable to integrate as many probe functions into one IC as possible in order to economize on space within the probe outer housing. Note that if data compression is not used, the need for a DSP is obviated, since other functions may be performed by the microcontroller  1025 . The DSP  1024  interfaces with the memory controller within the memory  1026  which controls the accessing and storage of data therein. The probe memory  1026  of the present embodiment is a standard 3.3. V logic static random access memory (SRAM), although other types of memory (such as DRAM, SDRAM, “flash”, or SLDRAM) may be used. 3.3. V SRAM is preferred based on its comparatively low power consumption and static data storage properties. The memory  1026  is chosen to have adequate storage capacity for compressed (or non-compressed) data output from the DSP  1024  during imaging. The memory  1026 , depending on the operating mode of the probe (e.g., streaming data externally via the data transfer sub-circuit, or storing internally), must be able to store a sufficient amount of data so as to permit (i) any buffering of the data necessitated by the data transfer sub-circuit  1026 , and (ii) storage of at least one frame (and preferably more) obtained by the CCD array  1010 . In the present embodiment, a sub-array of 31,680 pixels is used (192 pixels per line, 165 lines per sub-array); hence, a memory storage capacity corresponding to binary representations of at least this number of pixels is used. The memory storage capacity needed is further determined by the type and efficiency of compression utilized, if any. Compression is used not only to minimize the size and increase the capacity of the memory  1026  within the probe, but also to minimize the bandwidth necessary to transmit data via the data interface sub-circuit  1027 . 
     It will be recognized that while the foregoing descriptions of the smart probe of the present invention are cast in terms of embodiments having laser and/or broad spectrum visual light sources, a CCD array, inductive power and data transfer, and signal processing and/or data storage capability, any number of different combinations of these features (or even other features) may be used consistent with the present invention. For example, a probe having a laser diode, CCD array, capacitive data transfer, and battery power supply is contemplated. Alternatively, other embodiments of the smart probe could include a device for obtaining a microsample (biopsy) of intestinal tissue, or for delivering a dose of a drug, chemical, or even ionizing radiation to, inter alia, otherwise inaccessible portions of the intestine of the patient. A large number of alternate configurations are possible, all being within the scope of the present invention. 
     Endoscopic Delivery Device 
     Referring now to  FIG. 13   a,  a first embodiment of the endoscopic delivery device of the present invention is disclosed. Specifically, the device  1300  of  FIG. 13   a  includes a housing  1302  located at its distal end  1304 , the housing having an internal cavity  1306  sized to receive the smart probe  300  of  FIG. 3  (or alternatively, other embodiments). The housing  1302  and distal end of the device  1304  are sized so as to permit passage through the esophagus and stomach of a patient. The cavity  1306  is open at the distal end of the device, such that the smart probe  300  may be inserted into the cavity via an aperture  1308 . 
     A closure or diaphragm  1310  is mounted over the aperture  1308  as shown in  FIG. 13   a.  The closure  1310  is, in the present embodiment, a substantially hemispherical membrane which is scored or perforated in one or more areas of its surface so as to be substantially weakened in these areas (see  FIG. 13   b ). In one embodiment, the closure is scored radially as shown in  FIG. 13 . One or more tubes  1316  running down the length of the delivery device  1300  terminate in the cavity  1306  in the region  1312  behind the probe  300  (when inserted in the housing  1302 ). A pliable, ring-shaped seal  1314  is fitted to the interior of the housing near the aperture  1308 , the seal having an inner diameter of its sealing surface approximating that of the probe outer housing  302 . The seal  1314  is sized so as to permit easy movement of the probe  300  through the seal, yet also maintain adequate sealing against the gross leakage of fluid (or gas) past the seal. A non-toxic fluid or gas (such as water, or air) is applied via the tube(s)  1316  during implantation of the smart probe in order to expel the probe from the housing  1302  and cavity  1306 . Collectively, this arrangement comprises the release mechanism. 
     As the portion of the cavity  1306  behind the probe and seal  1314  is pressurized by the fluid/gas, the probe  300  is displaced forward within the cavity so as to contact the closure  1310 . The scores  1320  in the closure  1310  will eventually yield under the force exerted by the probe, thereby rupturing the closure and allowing the expulsion of the probe from the cavity. It will be recognized that the yield stress of the closure scores  1320  is preferably set such that an extremely low fluid/gas pressure is required to rupture the closure, thereby causing the probe  300  to move slowly out of the housing  1302  and preventing any potential trauma to the interior region of the patient&#39;s intestine from the expulsion transient. Additionally, the rate of pressure increase within the cavity  1306  can readily be controlled by the operator using any number of available means such as a hand pump, low volumetric flow rate mechanical pump, or the like. 
     While the present embodiment describes a mechanically ruptured closure and associated fluid system for expelling the probe, it can be appreciated that a number of different ways of rupturing or dissolving the closure may be employed. For example, minute electrical filaments could be used to melt portions of the closure prior to probe expulsion. Alternatively, the closure could be dissolved or weakened by the presence of one or more chemical agents, or even light energy. It will be further recognized that the closure is optional and may not even be used in certain applications, especially if a lens cover  308  is used on the probe  300 . 
     In the embodiment of  FIG. 13   a , a narrow fiber optic bundle  1322  and lens  1323  is routed around the periphery of the probe and within the housing  1302  of the endoscopic delivery device  1300  in order to assist the operator in locating and implanting the smart probe  300 . Light gathered by the bundle  1322  and lens  1323  is transmitted to a video display unit or other means of viewing (not shown). It will be recognized, however, that other means of viewing the probe  300  during delivery (both direct and indirect) may be used. For example, the probe/delivery device location could be viewed using ultrasonic, magnetic resonance, or X-ray imaging. 
     A second embodiment of the improved endoscopic delivery device according to the present invention is shown in  FIG. 14 . In this embodiment  1401 , the smart probe is biased by a spring or other means (such as an elastic member) toward the aperture  1408  in the housing such that the probe is urge from the cavity  1406  and housing  1402 , as shown in  FIG. 13   b.  A retaining detent or latch  1440  is positioned at or near the aperture  1408  and engages a recess  1442  in the outer housing  302  of the probe  300  such that when the probe is inserted into the cavity and latched, the spring  1446  (or other biasing means) biases the probe  300  against the latch  1440 . The latch is, in the present embodiment, actuated by a miniature cord or cable  1450  disposed within a channel  1452  running longitudinally up the side of the delivery device  1401 , although it will be recognized that a myriad of different release mechanisms may be used. Alternatively, an outer closure (not shown) may be used in place of the latch  1440  to retain the probe  300  within the housing against the biasing force until the closure is sufficiently weakened by electrical energy, light energy, or the presence of a chemical agent. 
     Method of Providing Diagnosis and Treatment 
     Referring now to  FIG. 15 , a method of providing diagnosis and treatment of a patient using the apparatus of the present invention is disclosed. 
     It will be recognized that while the following method recites a series of steps in a given order, this order may be permuted where appropriate such that the steps recited herein may be performed in alternate sequences. Additionally, certain steps (including, for example, the installation of the lens cover) may be completely omitted, or other steps added. The following description is meant only to be illustrative of the method of the present invention. 
     It will be further recognized that while not recited as a specific step in the embodiment of the method described below, patient intestinal preparation prior to introduction of the smart probe is essential to the proper operation of the probe while in the patient. Such intestinal preparations exist in a myriad of different varieties and are well understood by those of ordinary skill in the medical airs, and accordingly shall not be discussed further herein. 
     Additionally, while the following description of the method of the present invention is cast in terms of delivery via an endoscopic delivery device, it will be appreciated that other methods or forms of delivery device may be used, and that the method is not limited to one form of delivery. For example, the probe may be sized such that it can be swallowed by the patient. Ultimately, as the probe is passed through the stomach into the small intestine after swallowing, it will be oriented based on its shape (substantially ellipsoid or cylindrical in the preferred embodiments) so as to facilitate data gathering. 
     In the first step  1502  of the instant method  1500 , the type/configuration of probe to be used is determined based on the parameters of the patient and the information desired, and a testing protocol selected. For example, if only a visual inspection of a portion of the intestinal wall of a patient is desired, then a probe of the type described with reference to  FIGS. 3–7  above is selected. Such a probe can arguably have a smaller profile (due to its simpler construction as compared to the probe of  FIGS. 10–11 ), and therefore may be better suited in applications where intestinal strictures may exist. 
     The probe is then tested outside of the patient to verify proper operation in step  1504 . Such testing may include, inter alia, testing of the operability of the CCD array, laser diode and DSP (if so equipped), LED, data transfer circuit, and inductive power circuit. It will be recognized that a number of different test protocols may be used depending on, inter alia, the specific configuration of the probe. 
     Next, the proper lens cover is chosen for use with the probe and installed if desired in step  1506 . As previously discussed, the lens cap is in one embodiment comprised of a material which dissolves in the presence of one or more gastric substances (or due to other conditions such as exposure to coherent light energy). Information regarding the motility of the patient&#39;s intestinal tract, and the location of the region of prospective examination/treatment, may also be used in making the selection of the proper lens cover if appropriate. In the embodiment of  FIGS. 3–5 , the lens cap may simply be installed to fit within the recess around the lens  306 , as described above. 
     In step  1508 , the patient is optionally sedated using any number of techniques which allow the probe to be inserted (via the aforementioned endoscopic delivery device) into the esophagus of the patient. Sedation techniques are commonly used in endoscopic examination and are well known in the medical arts, and accordingly are not described further herein. 
     Next, in step  1510 , the smart probe  300  is introduced into the patient. In one embodiment of the present method, the probe is inserted using the specially adapted fiber optic endoscopic delivery device previously described. It will be recognized, however, that other methods of delivering and placing the probe can feasibly be used with equal success. 
     In the next step  1512  of the present method, the smart probe is tested in-situ while still retained within the housing of the delivery device  1300  to ensure proper data and/or power transfer between the external monitoring and control device (MCD)  800  and the probe. The probe  300  is first powered up using the inductive (or RF) signal applied from the MCD remote unit  802  via the power transfer circuit  700 . Then, the CCD and probe circuitry and LED circuitry is activated to generate ambient light and an image using the CCD array  402 . This image data is then transferred to the MCD via the data transfer circuit  600  to verify proper operation of the CCD and associated components. Optionally, the functionality of the laser  1012 ,  1013  and the autofluorescence CCD sub-array  402   b  (if so equipped) can be verified as well. Note that if the lens cover  308  is utilized, the image transferred will be blurry and out of focus due to the optical characteristics of the lens cover. However, the operation of the CCD and laser can be suitably verified even with the lens cover in place. 
     After proper operation of the probe  300  is verified, the probe is positioned and implanted within the patient in step  1514 . Ideally, the probe  300  is implanted in the ileum region of the patient&#39;s small intestine; however, other locations may be used. Implantation preferably occurs using the aforementioned fluid/gas pressurization technique which expels the smart probe  300  from the endoscopic device housing  1302 . 
     Next, the endoscopic delivery device  1300  is retracted from the patient in step  1516 . The smart probe  300  is then activated and tracked (or, alternatively, tracked and subsequently activated when the desired probe position is achieved, or maintained in an activated state continuously) in step  1518 . Tracking can occur in a number of ways including, inter alia, via direct feedback (i.e., by maintaining continuous data transfer between the probe and the MCD remote unit), or by using an ultrasound imaging system. 
     Next, in step  1520 , visual or autofluorescence image data is streamed out of the probe and/or stored, based on memory limitations, within the memory of the probe if so equipped. Note that if a lens cover  308  is utilized on the probe  300 , the lens cover must be dissolved prior acquiring image data. Furthermore, if a probe having the aforementioned laser module  1012 ,  1013  is used, and laser-excited autofluorescence data is desired, the laser diode will need to be activated for a period of time beginning prior to the acquisition of autofluorescence image data by the autofluorescence sub-array  402 b. 
     In step  1520 , data streamed from the probe  300  is processed and analyzed in the MCD  800 . Note that this step may be performed at a later time; i.e., the image data can be stored within the storage device  916  of the MCD or other external storage device for later analysis. 
     When all data acquisition is complete, the probe is deactivated (such as by simply by powering it down) in step  1522 . Lastly, in step  1524 , the probe  300  is retrieved from the patient via normal excretory function. Any remaining data stored in memory  1026  at that point may be retrieved using the MCD  800  and data transfer circuit  600  previously described, and subsequently analyzed. 
     While the above detailed description has shown, described, and pointed out novel features of the invention as applied to various embodiments, it will be understood that various omissions, substitutions, and changes in the form and details of the device or process illustrated may be made by those skilled in the art without departing from the spirit of the invention. The described embodiments are to be considered in all respects only illustrative and not restrictive. The scope of the invention is, therefore, indicated by the appended claims rather than the foregoing description. All changes that come within the meaning and range of equivalence of the claims are to embraced within their scope.