PATENT ABSTRACT
A device for illuminating a body cavity may include an elongate tube, at least one lens element, and at least one deployable element. The elongate tube may include an internal lumen extending between a distal opening at a distal end and a proximal opening at a proximal end opposite the distal end. The at least one lens element may extend substantially across a diameter of the internal lumen of the elongate tube. The at least one deployable element may include a light source. The at least one deployable element may be operably coupled to a region of the elongate tube proximate the distal end and may be configured to be moved between an insertion position and a deployed position.

PATENT DESCRIPTION
CROSS-REFERENCE TO RELATED APPLICATIONS 
     This patent application is a continuation of U.S. patent application Ser. No. 11/233,684, filed Sep. 23, 2005, which claims priority to U.S. Provisional Patent Application No. 60/612,889, filed Sep. 24, 2004. The foregoing applications are incorporated herein by reference. 
    
    
     TECHNICAL FIELD 
     The present invention relates generally to apparatus for the illumination of endoscopic and borescopic fields, in minimally invasive surgical (MIS) procedures, general or diagnostic medical or industrial procedures using endoscopes or borescopes, respectively. More particularly, embodiments of the invention relate to use of Light Emitting Photodiode and other solid state light sources in endoscopic and borescopic procedures, as a means of illumination. 
     BACKGROUND 
     Laparoscopy is used in both diagnostic and surgical procedures. Currently, MIS procedures, as opposed to open surgical procedures, are routinely done in almost all hospitals. Minimally invasive techniques minimize trauma to the patient by eliminating the need to make large incisions. This both reduces the risk of infection and reduces the patient&#39;s hospital stay. Laparoscopic and endoscopic procedures in MIS use different types of endoscopes as imaging means, giving the surgeon an inside-the-body view of the surgical site. Specialized endoscopes are named depending on where they are intended to look. Examples include: cystoscope (bladder), nephroscope (kidney), bronchoscope (bronchi), laryngoscope (larynx+the voice box), otoscope (ear), arthroscope (joint), laparoscope (abdomen), gastrointestinal endoscopes, and specialized stereo endoscopes used as laparoscopes or for endoscopic cardiac surgery. 
     The endoscope may be inserted through a tiny surgical incision to view joints or organs in the chest or abdominal cavity. More often, the endoscope is inserted into a natural body orifice such as the nose, mouth, anus, bladder or vagina. There are three basic types of endoscopes: rigid, semi-rigid, and flexible. The rigid endoscope comes in a variety of diameters and lengths depending on the requirements of the procedure. Typical endoscopic procedures require a large amount of equipment. The main equipment used in conjunction to the visual part of the endoscopic surgery are the endoscope body, fiber optics illumination bundles, illumination light source, light source controller, imaging camera, camera control module, and video display unit. 
     The laparoscope is a rigid endoscope as illustrated in  FIG. 1 . It allows for visualization of the abdominopelvic cavities for diagnostic or surgical techniques. The laparoscope is inserted into the peritoneal cavity via a cannula that runs through the abdominal wall. There are many different features of laparoscopes, such as the size and field of vision, which determine the effectiveness of the instrument. 
     As illustrated in  FIG. 1 , the basic laparoscope is made up of a long thin tube  101  with an eyepiece  103  at one end for viewing into the patient. Fiber optic light introduced to the endoscope at fiber port  102 , and launched into fiber optics  123  ( FIG. 3) and 138  ( FIG. 4 ), passes through the endoscope body  101 , illuminating the area  124  that is being observed, as illustrated by radiation pattern  125  in  FIG. 3 . Laparoscopes are characterized by diameter and the direction of view. The direction of view is the angle  107  between the axis of the laparoscope  105  and the center field of view  106 , as illustrated in  FIG. 1 . Typical endoscopes have lengths of approximately 30 cm and diameters in the range of 4 to 10 mm. Laparoscopes consist of two important lenses, the ocular lens at the eyepiece and the objective lens  122  at the distal end of the endoscope body  101  in  FIG. 3 . Other lens sets acting as relay lenses  121  in  FIG. 3 , are used in-between the objective lens and the eye piece or the CCD camera or image position  127 . Imaging rays  126  traverse the length of the scope through all the imaging optics. 
     The rigid endoscope also comes in different viewing angles: 120 degree or retrograde, for viewing backward; 90 degree and 70 degree for lateral viewing; 30 degree ( 104  as illustrated in  FIG. 1 ) and 45 degree for forward oblique views; and 0 degree for forward viewing. The angle of the objective lens  122  used is determined by the position of the structure to be viewed. 
     Other surgical instruments and tools are also inserted into the body, for the operation and specific surgical manipulation by the surgeon. The insertion is done through open tubes provided inside the endoscope body for instrument insertion, such as in gastrointestinal endoscopes, or through separate incisions in the abdominal or chest wall  113 , using cannula  110  (straight or curved stainless steel or plastic tubes  101  which are inserted into a small opening or incision in the skin as illustrated in  FIG. 2 ). The cannula opening  112   a  (receiving portion) at the proximal end  112  outside the body is used to receive and guide different instruments  300  inside the body, where they are exposed to the inside of the body at the distal end  111  (opening  111   a ) of the cannula  110  ( FIG. 2 ). Cannulas can make a seal at the incision site  114 . 
     In a typical gastrointestinal endoscope, a tool opening is provided at the distal end of the scope, where inserted medical instruments gain access to the body following the scope body. 
     Endoscopes can be diagnostic, for observation only, or operative, having channels for irrigation, suction, and the insertion of accessory instruments when a surgical procedure is planned. Thus, endoscope bodies also could provide mechanical or electrical control sections, buttons for valves such as a suction valve, a CO2 valve, a water bottle connector, a water feed, a suction port, etc. The common component that all endoscopes must be equipped with is a light guide section for illumination. 
     An illustration showing typical endoscope optics is shown in  FIG. 3 . Common imaging sections of the endoscope are an ocular or eyepiece, relay lenses  121  (in the case of rigid scopes), a flexible imaging fiber-optic bundle (in the case of flexible scopes), and an objective lens system  122 . Endoscopes are either used as stand-alone units, with the surgeon looking into the scope from the ocular or eye piece of the endoscope, or in conjunction with digital cameras  127 , where an image (rays  126 ) of the surgical site  124  is incident on the image capture device (charge coupled device or CCD) of the camera ( 127 ). Using a display device, the surgeon performs the operation looking at the image on the video monitor. 
     With recent technology improvements in the field of electronic imaging reducing the size of the image capture device (CCD), some endoscopes used in MIS and diagnostic procedures are equipped with a high resolution distal end camera system, commonly referred to as Chip on a Stick, one example of which is illustrated in  FIG. 4 . These flexible endoscopes use a CCD chip  137  at the distal end of the endoscope directly capturing the image through the objective lens  133 , in which case the flexible part ( 132 ) of the endoscope body, contains only power ( 137   a ) and communication wires  137   b  for the CCD camera at the distal tip, rather than imaging optics  133  which is located in the rigid portion  131  of the endoscope. Light guides  138  are still necessary for this type of electronic scope to provide adequate lighting ( 134 ) of the surgical site  136  for imaging purposes. 
     Other, more complicated MIS systems make use of robotic surgical tools and instruments, and/or provide stereoscopic images of the surgical site for the surgeon, improving the surgeon&#39;s dexterity, precision and speed of operation. In these more sophisticated MIS imaging applications more specific types of illumination systems or multiple illuminators are used. 
     Endoscopes can have a variety of forms, ranging in diameter, tube length, and angle of view. However, all types of endoscopes commonly use optical fibers ( 123 , and  138  in  FIGS. 3 and 4 ) to illuminate the surgical site. Illumination is a very important part of laparoscopy because there is no light source inside the body. Fiber optic cold light is used to project light down the laparoscope from an external source. Large lamps with broadband output are used to couple light into the illumination light guides ( 123  and  138  in  FIGS. 3 and 4 ), where light guides transfer the illumination light from the light source to the illumination fiber bundle ( 123 ,  138 ) inside the endoscope body  101 . A typical scope attached to an illumination light guide (port  102 ) is shown in  FIGS. 1 ,  3  and  4 . One ( FIG. 1 ) or more light guide bundles ( FIGS. 3 and 4 ) are used to couple light into the endoscope illumination fiber bundles  123  and  138  of  FIGS. 3 and 4 . 
     The use of fiber bundles  123  and  138  inside the endoscope body  101  in  FIG. 3  and  FIG. 4 , or tube  101  occupies substantial space that otherwise could have been used by the imaging optics. This can be seen in  FIGS. 3 and 4 , showing the fiber optic illuminators  123  and  138  sharing the endoscope body  101  with the imaging optics ( 121 ,  122 ,  133 ). Limitations on the optical lens terrain ( 121 ,  122 ,  133 ) diameter, as well as the imaging fiber bundle thickness, correlate directly to the imaging resolution vs. size of the image. The larger the lens diameter or imaging bundle thickness, the better the resolution of the endoscope for a certain field of view (FOV) or image size. This is the main reason that larger diameter scopes are considered better in optical quality than narrower scopes. However, large scope diameters are not desirable for certain operations where space is limited on the operation site. 
     Different illumination fiber geometries are used to reduce the space constraint inside the scope body. For this reason, and to have a more uniform illumination, the imaging fiber bundles are also split in some cases to have two or more points of illumination at the distal end of the scope. In other types of scopes, illumination is made into a circular ring pattern at least at the distal end of the endoscope, similar to the ring illumination of microscopy. 
     The light source for the endoscope is either a xenon bulb, which creates a high intensity white light suitable for smaller-diameter endoscopes, a halogen bulb, which creates a yellowish light suitable for general endoscopic work, or a Metal Halide lamp. Since most broadband light sources also produce large amounts of Infrared Red (IR) wavelength light, IR cut filters and lamp dichroic reflectors (heat blocking filters and reflectors that reduce the radiation usually associated with heat production) are used in the illumination light source to prevent the transfer of IR radiation to the body. Thus, broadband visible cold light is highly desirable in laparoscopic procedures providing decreased thermal injury to tissues. Since most CCD cameras are also sensitive to IR radiation (due to Silicon absorption spectrum), extra IR cut filters are used in front of the camera to prevent glare caused by IR radiation in the camera. 
     Despite the precautions used in reducing the IR radiation, in actuality some amount of infrared radiation in addition to the visible light enters the fiber optic cable, and is transmitted through the cable and scopes (port  102 , fibers  123  and  138 ) into the body. When the light leaves the endoscope tip, the level of infrared radiation has usually been reduced to a safe level through absorption by the optical fibers in the endoscope, and substantial losses at the cable connections (port  102 ). However, if the cable is not connected to the endoscope, the infrared output is not reduced sufficiently and even could have the capability of igniting some materials if the cable is left at close proximity to absorbing combustible material. This hazard exists in fiber illumination cables with high intensity light sources. 
     Additionally, higher outputs not only increase the risk of fire, but may introduce the risk of burns during close-range inspection of tissue with the endoscopes. Absorption of high-intensity radiation at visible light wavelengths may also cause tissue heating, where additional filtering of infrared wavelengths may not eliminate this hazard. Furthermore, with the increasing use of television systems with video cameras connected to the endoscopes, many physicians operate light sources at their maximum intensities and believe they need even greater light intensities to compensate for inadequate illumination at peripheral areas of the image where the illumination intensity falls rather rapidly using today&#39;s standard illumination fiber guides. 
     Typical light sources are also deficient in their flux and color management of their spectral output. A typical lamp spectral output requires time to come to an acceptable level during the warm-up procedure, both in terms of lumens output as well as color quality or white point on the color gamut. The color temperature of the lamp based illuminators, are typically deficient in producing the desirable color temperature (daylight color temperature of 5600 Kelvin) for typical endoscopic procedure. Color content of the lamp output also typically shifts during the life time of the lamp. Thus it is usually required to perform a white color balance adjustment in the camera controller each time an endoscope is used subsequent to the light source warm-up procedure to obtain realistic color image. A repeat of the white color balance adjustment may also be necessary if the lamp intensity is adjusted through a large range. 
     Typical high power lamps also have very limited life time, measured in hours (Typically 50, 500, or 1000 hours for Halogen, Xenon or Metal Halide depending on the lamp), where the light output of the lamp degrades to about one half of its original light output. Typical lamp manufacturers typically do not specify or have a failure criteria based on the color quality for the lifetime of the lamp. 
     Complicated and bulky optical schemes are incorporated in the light guide optical sources for effective coupling of the light into the illumination fiber bundles ( 123  and  138 ). Special non-imaging optics such as glass rods, and lens elements are used to also uniformly couple light into all the fibers inside the illumination fiber bundle. All these increase the cost and also size of having high brightness, uniform fiber optic illumination light sources. Typical high brightness light sources also incorporate powerful fans to dissipate the large amount of heat generated inside the light source package. In fact in a typical endoscopic procedure, light sources are one of the main sources of heat generation and the associated fans on the light sources are one of the main sources of noise in the surgical environment. Large package size of high power lamps also add extra burden to the premium space in a diagnostic and surgical environment. 
     Light sources normally give off electromagnetic interference (EMI), where the starting pulses from the lamp could reset or otherwise interfere with other digital electronics devices in today&#39;s surgical environment. 
     In an operating environment, the light source(s) are placed at a distance, on a table top or rack, mounted away from the patient and the endoscope. Fiber optic light bundles to transfer the light from the light source to the endoscope are used as light links between the light source and the endoscope. These fiber bundles are not only bulky and expensive, but their price increases by the length of the fiber bundle, whereas the amount of light transmitted goes down as the length of the fiber bundle increases. To conveniently place the light source and fiber bundle away from the operational site, longer fiber bundles are necessary, however the attenuation, or drop in the transmitted optical flux increases with the length of the fiber used as well, requiring more powerful light sources. 
     Use of fiber optic light guides as a means of transfer of illumination light from the proximal  122  to the distal end  111  of the endoscope also increases the chance of relative light loss. The relative optical light-loss measurement quantifies the degree of light loss from the light source to the distal tip of the endoscope. The relative light loss will increase with fiber-optic ( 123 ,  138 ) damage. Extra heat will also be generated in the broken fiber ends inside the endoscope. In fact the major failure mode for the fiber optic bundles delivering the light to the endoscope, and the optical system inside the endoscope is breakage of the fibers. 
     As illustrated in  FIGS. 1 ,  3  and  4 , the illumination fiber bundle(s) port  102  commonly join the endoscope body at some angle near the ocular ( 103 ) at the proximal side  112  of the endoscope. The fiber guide body and the main endoscope body  101  are commonly joined together in a welding process at joint  108  illustrated in  FIG. 1 . The construction and design of this welded joint is often a weakness in the endoscope manufacturing and use, where after many operations, high temperature and high humidity sterilizations, and successive handling, this welded joint could get damaged and break, exposing the internal parts of the scope to the environment when the seal is broken. 
     Color CCD cameras use alternate color dies on the individual CCD pixels, to capture color images. Green and red, and green and blue pixels are alternated in rows. This spatial color sampling limits the color resolution of the color CCD cameras, since each pixel is dedicated to capturing a single color in the color image. 
     Three (3) chip CCD cameras (red CCD chip, blue CCD chip, and green CCD chip) are also used in high resolution applications, where all the pixels in each CCD are dedicated to detecting the single color content of the image. The individual color captured images from the 3 CCDs are then put together electronically, as the multi-color image is reproduced on the viewing display. Three chip CCD cameras are expensive and bulky. 
    
    
     
       BRIEF DESCRIPTION OF THE DRAWINGS 
       To further clarify the above and features of the present invention, a more particular description of the invention will be rendered by reference to specific embodiments thereof which are illustrated in the appended drawings. It is appreciated that these drawings depict only typical embodiments of the invention and are therefore not to be considered limiting of its scope. The invention will be described and explained with additional specificity and detail through the use of the accompanying drawings in which: 
         FIG. 1  illustrates a typical angled endoscope, with fiber optic light port for illumination, and an eye piece for viewing; 
         FIG. 2  illustrates a cannula inserted into the body cavity, providing means to insert an instrument into the body. 
         FIG. 3  illustrates the cross section of a typical zero degree, rigid endoscope with associated terrain for relay of the image through the length of the endoscope; 
         FIG. 4  illustrates the cross section of a zero degree typical flexible endoscope body (Chip on the Stick) with fiber optics illumination; 
         FIGS. 5   a  to  5   d  illustrate various single LED sources, without and with various encapsulation optics; 
         FIGS. 6   a  and  6   b  illustrate a self-lighted cannula using multiple LED sources installed at the proximal end of the cannula; 
         FIG. 7  illustrates a cannula body used as the illuminator for inside the body cavity; 
         FIG. 8  illustrates a cannula with built in LED illuminators at the distal end of the cannula; 
         FIGS. 9   a  and  9   b  illustrate an angled endoscope with modified distal tip, incorporating an array of LEDs for illumination of the surgical site; 
         FIG. 10  illustrates fixed solid state illuminators assembled behind the first negative lens of the endoscope, used as window at the distal end of a flexible endoscope; 
         FIGS. 11   a  and  11   b  illustrate inclusion of the LED sources within the objective lens of an endoscope, using a beam splitter; 
         FIGS. 12   a  and  12   b  illustrate insertion and deployment of a flexible membrane with built in LED illuminators, to light the surgical area inside the body; 
         FIGS. 13   a  and  13   b  illustrate possible deployment of LED illuminators at the distal end of a flexible endoscope; 
         FIGS. 14   a  and  14   b  illustrate possible deployment of LED illuminators stored within the objective lens of a flexible endoscope; 
         FIGS. 15   a  and  15   b  illustrate possible deployment of LED illuminators stored next to the objective lens of a rigid body endoscope; 
         FIGS. 16   a  and  16   b  illustrate possible deployment of LED illuminators stored along the distal tip of a rigid body endoscope; 
         FIGS. 17   a ,  17   b , and  17   c  illustrate LED illuminators built into the body of a surgical instrument or tool, with possible deployment during operation to illuminate the surgical site. 
     
    
    
     DETAILED DESCRIPTION 
     Exemplary embodiments of the invention concern monochromatic or polychromatic solid state light sources such as high power Light Emitting Devices (LEDs) and Laser Diodes as a means of illumination in a diagnostic or surgical endoscopic procedures, or functional borescopic systems. In particular, these solid state light sources are incorporated at the distal end of the endoscope, borescope, surgical or industrial tools, and the tip end of cannulas and other functional devices. They can also be incorporated in an illumination body that is inserted separately, or in conjunction with a lighted or dark scope, into the body. The illumination of an object inside a body, a body herein being defined as at least a portion of a human, animal or physical object not easily accessible, is performed to detect the modified light, image the object, or manipulate a change in the object. The solid state illumination schemes of the present invention can replace, or can be used in addition to, the conventional fiber optic illumination system and other diagnostic devices such as ultrasound imaging used in endoscopy and borescopy. 
     Use of such solid state sources inside a cavity in the body, replaces variety of instruments otherwise needed for the same purpose, such as an external light source, fiber light guides, and means of transmitting the light to the desired object. 
     Exemplarily, the use of LED sources has several advantages over the conventional external white light source. With an LED based illumination, a true, visible light source with no IR content is available for the endoscopic application. Therefore, the complicated IR management of the light source is eliminated. There is no longer a fire hazard associated with light guides that may be left on, and no heat management inside the scope is needed. 
     LEDs can provide light at any region of the visible spectrum. Red, Green, and Blue LEDs (chips) in primary colors can be used together to form a white illumination, Phosphor-converted LEDs can provide white output directly without any color mixing, Infra Red (IR) or Ultraviolet (UV) LEDs can be used for their special characteristic in light transmission in the medium of insertion or the effect they have on the object of interest ( 151 ,  161 ,  171 ,  181   b ,  191 ,  201   b ,  203 ,  205 ,  210   b ,  220   b ,  230   b ,  240   b ,  250   a  in  FIGS. 6   a  through  17   c ). 
     LED lifetimes are more than order of magnitude longer than bulb type light sources (50 k hours depending on the drive condition). The long life time in conjunction with the reliability associated with solid state lighting practically illuminates any lamp outages in an MIS procedure, where dependable illumination is one of the most critical parts of the system. In fact LED life time is more in line with the usage life time of most MIS surgical tools. 
     LED power consumption is also much lower than high power light sources. The LED illumination system is most efficient since there is no need for i) transferring light from the source through fiber optic light guides, ii) coupling the light into the scope light guides, or iii) transmitting through the fiber optic light guides through bends in the fiber. Light powers in the order of 1000 lumens are in fact possible with use of few high power LEDs. 
     Further, LEDs are robust, and do not break, unlike fiber optic light guides ( 123 ,  138  in  FIGS. 3 and 4 ). Properly encapsulated LEDs (chips), can withstand severe environmental conditions and cleaning procedures. 
     LEDs do not produce any electromagnetic interference, thus eliminating the need for complicated EMI management system such as Faraday caging. Because of size, reliability and safety of LEDs, these light sources are ideal choice for “in location” illumination of the object inside the body. Where only electrical power is transmitted to the light source inside the body along with possible electrical control signals. 
     By eliminating conventional fiber optic illumination guides  123  and  138  ( FIGS. 3 and 4 ) inside the endoscope body  101 , there is more space for the imaging optics ( 121 ,  122 ,  133 ) or imaging fibers, where the size directly relates to the image information transfer capability of the system. With more space available to the imaging optics ( 121 ,  122 ,  133 ), larger diameter optics and imaging fiber diameters can be used, making larger image FOVs (made by imaging rays  126  and  135 ) and higher resolution possible. 
     LEDs do not require a warm-up procedure. LEDs are capable of providing instant illumination with the exact color point at initiation. Optical power and color maintenance over the life time of the LED are also critical features of solid state light sources. 
     By using three color LEDs (red, green and blue chips) and synchronizing a black and white camera system to grab the three synchronized color component images ( FIGS. 6   a  through  17   c ), the use of color camera chips or the high resolution 3 CCD chip cameras is eliminated. Since a single CCD camera is used to capture the three images in a time synchronized fashion, each color component image takes advantage of the full CCD image resolution by incorporating all the pixels in each color image component. Examples of exemplary embodiments of endoscopes having LED illuminators ( 191 ,  201   a ,  201   b ,  203 ,  210   a ,  220   a ) and CCD image cameras  137  are shown in  FIGS. 4 ,  10 ,  11   a - b ,  13   a - b , and  14   a - b . Simple black and white CCD or CMOS camera chips ( 137 , in  FIGS. 10 ,  11   a - b ,  13   a - b ,  14   a - b ) are also cheaper to use, especially compared to a 3 chip CCD camera, where in effect the resolution of the synchronized black and white imaging CCD using synchronized color illumination ( 191 ,  201   a ,  203 ,  210   a ,  220   a ) provided by the LED chips ( 191 ,  201   b ,  203 ,  210   b ,  220   b ) is equivalent to a same pixel 3 CCD chip camera ( FIGS. 10 ,  11   a - b ,  13   a - b ,  14   a - b ). 
     Using the color synchronized image capture device also allows the use of much higher resolution image capture devices in chip on the stick cameras ( 137 , in  FIGS. 10 ,  11   a - b ,  13   a - b ,  14   a - b ) where space is limited at the distal tip of the endoscope  190  for the image capture CCD. A variety of illumination configurations are possible using LED chips, where the uniformity, angle and extent of the illumination are freely controlled by the positioning and design of the LED light sources ( 191 ,  201   a ,  203 ,  210   a ,  220   a ). 
       FIGS. 5   a  through  5   d  illustrate various configurations of LED output.  FIG. 5   a  depicts a LED  140  disposed on a base  141 . The LED  140  is unencapsulated resulting in output in the form of a Lambertian light source. This makes these solid state light sources ideal for endoscopic illumination applications where wide angular field of view needs to be properly illuminated. 
     A simple lensing element can also be used in the form of an LED encapsulant, where depending on the shape of the lens surface and the lens&#39; distance from the LED surface, different angular illuminations or focusing of the light can be easily accomplished.  FIG. 5   b  illustrates a simple lens encapsulation  143  maintaining the same Lambertian light output as the unencapsulated LED, however with much higher light extraction from the LED chip. 
       FIG. 5   c  depicts an alternate surface structure for the LED encapsulation, such as fresnel lens profile  144 , diffractive optics or other refractive profiles can yield different angular extent of the encapsulated LED radiation pattern  144 . 
       FIG. 5   d  illustrates a simple lens encapsulation where higher index encapsulation material is used in conjunction with positioning the lens surface farther away than the lens radius of curvature resulting in a substantial decrease in the angular extent of the radiation pattern  146  can be achieved. 
     With controllable illumination color available to 3 color chip LEDs (in  190 ,  201   a ,  203 ,  210   a ,  220   a  of  FIGS. 10 ,  11   a - b ,  13   a - b ,  14   a - b ), the color gamut of the illumination can be changed according to the application using the drive condition for the independent color chips  190 ,  201   b ,  203 ,  210   b ,  220   b . This is highly desirable where the information content of the surgical site  136  is mainly in a certain color, and where shifting the illumination color can increase the visibility and differentiation needed in diagnostic evaluation of the surgical scene. 
     Using more illumination sources (more LED chips in  FIGS. 5   a - 5   d ) with other wavelengths than the three primary illumination colors, and matching the image detection ( 137 ) frame capture sequence to that of the synchronized color illumination sources ( 191 ,  201   b ,  203 ,  210   b ,  220   b , in  FIGS. 10 ,  11   a - b ,  13   a - b ,  14   a - b ), allows higher quality image capture in terms of more realistic colors. Using only primary RGB colors (RGB chips  151 ,  161 ,  171 ,  181   b ,  191 ,  201   b ,  203 ,  205 ,  210   b ,  220   b ,  230   b ,  240   b ,  250   a  in  FIGS. 6   a  through  17   c ) the detected image color content is within the color triangle in the CIE color diagram. Adding LED chips with other colors such as amber, cyan, and magenta, increases the detected color gamut of the image substantially. With the recent color displays such as flat panel LCD displays using more than just primary color illuminators (such as with 6 LED back light illuminators), it is in fact possible to present a “true color” image to the operator that was never before possible with the 3 color CCD cameras. This can be important in certain surgical applications where the color reproduction integrity plays an important role in the surgeon&#39;s perception of the scene or diagnosis of the object. 
     LED illumination systems are modular, where one or multiple LED chips ( 151 ,  161 ,  171 ,  181   b ,  191 ,  201   b ,  203 ,  205 ,  210   b ,  220   b ,  230   b ,  240   b ,  250   a  in  FIGS. 6   a  through  17   c ) can be inserted into the body independent of one another, via separate illumination bodies, at the distal end of an endoscope ( 180 ,  190  in  FIGS. 9   a - b ,  10 ,  11   a - b ,  13   a - b ,  14   a - b ,  15   a - b  and  16   a - b ), or incorporated at convenient and efficient locations on surgical tool tips ( FIGS. 17   a - c ) or cannulas ( FIGS. 6   a - b ,  7 ,  8  and  12   a - b ). 
     Different solid state light sources or combination of these sources can be used to perform diagnostic as well as surgical or other functions on a body. A variety of illuminators can work in conjunction with one another and other devices to image, detect or modify the object. 
     One example of an embodiment  150  of an LED illuminator according to the present invention used in a cannula body  101  is illustrated in  FIGS. 6   a  and  6   b . In this exemplary embodiment, the body  101  of the cannula  150  which is clear to the light in the visible spectrum is completely lit by white or color LED chips  151  mounted at the proximal end  112  of the cannula body  101 . Electrical power to the LEDs is provided by power connection  152  (electrical lines  152   a ) on body  101 . As illustrated in  FIG. 6   b , the LED light fed into the cannula body  101  goes through Total Internal Reflection as it travels the length of the cannula body  101  to the distal end  111 , at which point the light leaves the cannula body  101 , illuminating the surgical site and tools as indicated by radiation pattern  154 . 
     In an alternative embodiment of a cannula  160  depicted in  FIG. 7 , the cannula body  101  includes near its distal end  111  surface mount white or color chips  161 . A cone type reflective cover  162  for these LEDs  161  can also be inserted along with the cannula  160  into the body, where the LED light from the body  101  of the cannula is directed more towards the distal end  111  of the cannula  160 . 
       FIG. 8  illustrates another simple embodiment of a cannula  170  with white or color LED chips  171  mounted directly at the distal end  111  of the cannula  170 . 
     As depicted in  FIGS. 9   a  and  9   b , in an exemplary embodiment of an LED illuminated endoscope  180 , an array of white or color LED (chips)  181   b  is built into an extension portion  181   a  extending from the distal tip ( 111 ) of an angled endoscope body, tube  101 . The array of LED chips  181   b  can be encapsulated with lens elements  182  to establish the desired illumination field and uniformity  184 .  FIG. 9   a  illustrates this exemplary embodiment of endoscope  180  in the side view, and  FIG. 9   b  is and end view illustration of such embodiment. Clear imaging port is noted as  183  on these figures (with proximal opening  112   a  and distal opening  111   a ), and the LEDs ( 181   b ) are encapsulated using a Fresnel type lens structure  182 . Other tool insertion ports, multiple imaging ports for stereo imaging, or imaging ports with various Field of View (FOV), can be used in the clear area of the distal end (distal opening  111   a ) of the endoscope hollow tube  101 . Other solid state light sources such as laser diodes or various wavelength LEDs  181   b  can be mounted in the vicinity of the LED sources depicted in this embodiment to perform other functions using the same device. Other forms of optics or optical elements such as lenses, polarizers and wave-plates can also be used in front of the LED illuminators  181   b  or detection ports (distal end opening  111   a ) to modify the illumination extent or for proper detection of the light. 
     In an embodiment of a solid state illumination within a flexible endoscope  190 ,  FIG. 10  illustrates the incorporation of white, color LEDs or lasers, IR or UV solid state light sources (chips)  191  behind the first negative lens  193  of the objective lens  133 . This portion of the objective lens  193  in effect acts as a window ( 193   a ) for the illumination sources  191  (as well as imaging rays  135  as depicted in  FIGS. 10 ,  11   a - b ,  13   a - b ,  14   a - b ,  15   a - b  and  16   a - b ), since the concave portion of the first negative lens of the objective, is typically much smaller than the distal window of the scope. Solid state illumination sources in this configuration can be directly mounted to this glass window around the concave area of the lens. As the illumination light leaves the glass at the distal end, the angular radiation pattern  192  of the light expands as illumination is emitted outside the glass. Refractive, polarization, or wave-plates can also be implemented in the area of the negative lens  193  beyond the concave portion ( 193   a ) to modify the illumination characteristic. 
     In yet another embodiment of LED illumination ( 201   a ) within the endoscope  190 , white or combination of RGB LED chips,  201   b  can be used within the objective lens  133 . As illustrated in  FIG. 11   a , LEDs  201   b  can be mounted so that the illumination  192  crosses the endoscope imaging axis  106  (center of imaging rays  135 ), where the illumination light from the LEDs  201   b  is combined into the imaging path (axis  106 ) using beam splitter optics  202 . 
       FIG. 11   b  illustrates an alternative positioning of the LEDs  203  within the objective lens  133  in LED illuminated endoscope  190 , without the use of a beam splitter. Light emitted by the LEDs  203  in this geometry pass through the distal portion  111  of the objective lens  133 , illuminating the surgical site  136  through the same window ( 193   a ) as the endoscope imaging optics  133  (imaging rays  135 ). 
     LEDs provide a desirable cost advantage over conventional lamp and fiber guide systems, as it replaces the expensive light sources, long fiber optic light guides to transfer light from the light source to the scope port  102 , and the illumination light guides ( 123  and  138  in  FIGS. 3 and 4 ) inside the scope body  101  as well. Low level power is only needed for the LED light sources, thus the electrical connection of the LEDs  152  is much easier (over the hollow tubular body  101  as seen in  FIGS. 6   a - b ,  7 ,  9   a ,  10 ,  11   a - b ,  13   a - b ,  14   a - b ,  15   a - b  and  16   a - b ,  17   a - c ). 
     In each of the embodiments depicted in  FIGS. 9   a - b ,  10 ,  11   a - b ,  13   a - b ,  14   a - b ,  16   a - b  only electrical power  152  and LED control signals need to be provided for the endoscope, eliminating the heavy and bulky fiber optics illumination cable connection ( 102 ) to the scope ( 130  and  140  in  FIGS. 3 and 4 ), increasing the maneuverability of the endoscope. LED illumination systems are also more robust to shock and vibrations or extreme environmental conditions than the fiber optic illumination systems ( 123  in  FIG. 3 , and  138  in Figure). 
     Since any heat generated from the LEDs is not in the form of radiative heat, as in the case of lamps, it can be easily conducted out of the endoscope, or instrument tip ( 111  in  FIGS. 7 ,  8 ,  9   a - b ,  10 ,  11   a - b ,  13   a - b ,  14   a - b ,  15   a - b,    16   a - b ,  17   a - c ) using a conductive layer or the endoscope or instrument body ( 101 ) itself. Some of this heat can in fact be conducted towards the endoscope optical window  193   a , such as in the embodiment of  FIG. 10  which shows endoscope  190 , where the LEDs  191  are at intimate contact with the endoscope window  193   a  and its holder (in  FIGS. 13   a - b ), which provides the proper temperature setting to avoid any condensation on the optical window  193   a , during operation and additionally warms the distal end  111  of the cold endoscope  190  when it is inserted into the warm and humid body cavity. In turn a separate low power infrared LED can also be used for the purpose of heating the endoscope tip. 
     In addition to the above exemplary embodiments  180  and  190  ( FIGS. 9 ,  10 ,  11   a - b ), where the LED illuminators are used in fixed positions within the endoscope body  101 , other deployable embodiments ( FIGS. 12 ,  13   a - b ,  14   a - b ,  15   a - b ,  16   a - b , and  17   a - b ), are possible for effective illumination of the surgical site  136 . In these deployable embodiments, the LED illuminators ( 205   a ,  210   a ,  220   a ,  230   a ,  240   a ,  250   a , all mounted at the distal end  111  of the hollow tubular body  101 ) are deployable from an insertion position in which they are held within the insertion body ( 101 ) or within a close profile of the insertion body ( 101 ), to an operational position where they are conveniently pointed to the object of interest. In operational position, the illumination light  192  can be directed to the surgical site  136  from beyond the endoscope body  101 , where deployment of the LED holder structure positions the illuminators off axis from the imaging axis  103  (center of imaging rays  135 ), increasing the collection efficiency of the imaging optics. 
     In some exemplary embodiments, this deployment can be accomplished using, by way of example and not limitation, an umbrella type deployment structure capable of being opened and closed by an operator. Different variations of this umbrella structure can be used depending on the desired application, amount of illumination, and light positioning requirement.  FIG. 12   a  illustrates one example of an umbrella-type deployment structure where an LED-supporting structure  205   a  is deployed through cannula  200  (with cannula body  101 , distal opening  111   a , and proximal opening  112   a ). A circular flexible membrane  205   a  is populated with white or color LED chips  205 . This populated membrane  205   a  includes a spring at its peripheral section (circular edge  205   b ) of the membrane body  205   a . The membrane  205   a  is deployably coupled to the distal end  111  of the cannula  200 . In the insertion position, the membrane  205   a  is collapsed into a tube form (inside body  101  in  FIG. 12   a ). Once the collapsed membrane  205   a    FIG. 12   a , is maneuvered to the desired location, the membrane is fully deployed until it is outside the distal end  111  (opening  111   a ) of the cannula  200 . The spring action at the membrane&#39;s edge  205   b  forces the membrane to open into a flat surface  205   a  in  FIG. 12   b . LEDs  205  illuminate the surgical site where other tools and instruments  300  can be inserted into the body through hollow tubular body  101 . 
       FIGS. 13   a  and  13   b  illustrate another embodiment of dynamic deployment of LED illuminators  210   a . In  FIG. 13   a  LED illuminators  210   a  are shown in their “LED off” or insertion position. In order to deploy LEDs  210   b  (encapsulated by lens  182 ), the illuminators  210   a  are flipped over the endoscope tip (around hinges  211 ). Once the illuminators  210   a  are deployed (“LED on” position), the  210   b  LEDs are flipped into position around the endoscope  190 , distal tip  111 , as shown in  FIG. 13   b.    
     In another embodiment of deployable LED illumination,  FIG. 14   a  represents an “LED off” position for the LED illuminators  220   a  as they are stored within the endoscope objective lens free cavity. In an “LED on” position, LED chips  220   b  are deployed in a circular manner, rotating outside the objective lens  133  cavity of the endoscope  190 . 
       FIGS. 15   a  and  15   b , represent anther scheme in storing  230   a  LED illuminators in their “LED off” position, next to the objective lens  122  at the distal end  111  of the endoscope body  101 , in  FIG. 15   a . LEDs illuminators  230   a  are disposed on a hinge portion  232 . The hinge portion  232  is, in turn, connected to an actuation portion  233 . The LED illuminators  230   a  are deployed into position as the actuation portion  233  is pushed distally in the direction of the arrows towards the distal tip  111  of the endoscope. Such action deploys the hinge portion  232  which positions the LED chips  230   b  to emit light that is off-axis from the imaging optics axis  106 ,  FIG. 15   b.    
     In an alternate configuration, represented in  FIGS. 16   a  and  16   b , another type of deployment mechanism is used. The LEDs illuminators  240   a  are disposed on hinge portion  242 . The hinge portion  242  is, in turn, connected to an actuation portion  243 . The LED illuminators  240   a  are deployed into positions by pulling the actuation portion  243  proximally in the direction of the arrows toward the proximal end  112  of the endoscope  180 , deploying the LED chips  240   b  into their “LED on” position. 
       FIGS. 17   a  through  17   c  illustrate an exemplary embodiment of LED illumination tubular body  101 , in conjunction with a surgical tool  300   b .  FIGS. 17   a  and  17   b  are side views of the surgical tool in an illumination “off” position.  FIG. 17   c  illustrates surgical tool  300   b  in an illumination  250   b  or deployed “LED on” position, where LEDs illuminators  250  are opened up from the stored position to illuminate the surgical work area. 
     In alternate embodiments of all of the endoscopes, cannulas and other devices (body  101 ) described above ( FIGS. 6   a  through  17   c ) that use LEDs for illumination, Solid State Laser Diodes (LD) can also be used at the distal end of tools, insertion tubes, catheters, imaging scopes, cannulas, etc. Infrared Imaging could use IR solid state light sources to illuminate intra-vein or close tissue diagnostic and surgical procedures. IR detectors and cameras are used for thorough tissue and blood imaging along with external infrared light sources that have appreciable penetration depth in human tissue, blood or other bodily fluids such as urine. Using a high intensity IR source at the surgical or examination site with control over the intensity, radiation pattern, and the direction of illumination helps with the most critical surgical procedures inside the vein, heart and other body organs. 
     Scanning or other directing mechanical elements  300  could also be used (inserted through the proximal opening  112   a ) to adjust the direction of illumination and control of the solid state light sources (laser diodes, and LEDs) used in conjunction with variety of surgical instruments inside the body ( FIGS. 11   a - b ,  13   a - b ,  14   a - b ), where other scanning or non-scanning image capture elements detect the light. Additionally, since power (from  152 ) is provided to the solid state light source at the distal end  111  of the probe or scope  101 , resistive heat from part of the electrical signal can also be used to reduce condensation at the probe or scope window  193   a  in  FIGS. 9 ,  10 ,  11   a - b ,  13   a - b ,  14   a - b ,  15   a - b  and  16   a - b.    
     By placing the illumination light sources at close proximity of the object inside the body (distal end  111 ) in diagnostic or surgical procedures ( FIGS. 6   a  through  17   c ), the losses in conjunction with the transmission of light from the external source to the surgical site is eliminated. Thus, light sources that have equal efficiency in converting electrical power to useful light, can be operated in much lower input power, eliminating the need for sophisticated power and heat management. Power and control signals (from electrical connection  152 ) transmitting through appropriate wires and flex circuitry ( 152   a ,  137   a ,  137   b ), can be easily routed along the tool or endoscope body  101  to the light source (LED chips  151 ,  161 ,  171 ,  181   b ,  191 ,  201   b ,  203 ,  205 ,  210   b ,  220   b ,  230   b ,  240   b ,  250   a  in ( FIGS. 6   a  through  17   c ). 
     Miniature, optical components such as lenses ( 182 ), mirrors ( 162 ), beam splitters ( 202 ), polarizers, waveplates, etc. can also be used in conjunction with solid state light sources (laser diodes and LEDs), to further manipulate the illumination characteristics of the light. Lenses ( 182 ) for example, can be used to direct the light to larger or smaller areas of the scene  124  and  136 , or focusing the beam to a small area on the object depending on the application. 
     Polarization characteristics of the solid state laser or polarized LED light output can also be used in special detection schemes, where depth perception or other biological imaging characteristics that depend on the polarization of the light can be better perceived, similar to polarized microscopy. 
     The present invention may be embodied in other specific forms without departing from its spirit or essential characteristics. The described embodiments are to be considered in all respects only as illustrative and not restrictive. The scope of the invention is, therefore, indicated by the appended claims rather than by the foregoing description. All changes which come within the meaning and range of equivalency of the claims are to be embraced within their scope.