Patent Publication Number: US-2022239878-A1

Title: Endoscopic image enhancement using contrast limited adaptive histogram equalization (clahe) implemented in a processor

Description:
CROSS-REFERENCE TO RELATED APPLICATIONS 
     The present application relies on, for priority, the following United States Provisional Patent Applications, which are also herein incorporated by reference in their entirety: 
     U.S. Provisional Patent Application No. 62/162,788, entitled “Chromoendoscopy with Implementation of a Contrast Limited Adaptive Histogram Equalization (CLAHE) Algorithm in a Field Programmable Gate Array (FPGA)” and filed on May 17, 2015; and 
     U.S. Provisional Patent Application No. 62/259,683, entitled “Image Enhancement with Implementation of a Contrast Limited Adaptive Histogram Equalization (CLAHE) Algorithm in a Field Programmable Gate Array (FPGA)” and filed on Nov. 25, 2015. 
    
    
     FIELD 
     The present specification relates generally to endoscopy systems and more particularly, to a multiple viewing elements endoscopy system that enhances imaging by implementing a contrast limited adaptive histogram equalization (CLAHE) algorithm in a processor, preferably a field programmable gate array (FPGA). 
     BACKGROUND 
     Endoscopes have attained great acceptance within the medical community since they provide a means for performing procedures with minimal patient trauma while enabling the physician to view the internal anatomy of the patient. Over the years, numerous endoscopes have been developed and categorized according to specific applications, such as cystoscopy, colonoscopy, laparoscopy, and upper GI endoscopy and others. Endoscopes may be inserted into the body&#39;s natural orifices or through an incision in the skin. 
     An endoscope is usually an elongated tubular shaft, rigid or flexible, having a video camera or a fiber optic lens assembly at its distal end. The shaft is connected to a handle which sometimes includes an ocular for direct viewing. Viewing is also usually possible via an external screen. Various surgical tools may be inserted through a working channel in the endoscope for performing different surgical procedures. 
     Endoscopes, such as colonoscopes, that are currently being used typically have a front camera for viewing the internal organ, such as the colon, an illuminator, a fluid injector for cleaning the camera lens and sometimes also the illuminator, and a working channel for insertion of surgical tools, for example, for removing polyps found in the colon. Often, endoscopes also have fluid injectors (“jet”) for cleaning a body cavity, such as the colon, into which they are inserted. The illuminators commonly used are fiber optics which transmit light, generated remotely, to the endoscope tip section. The use of light-emitting diodes (LEDs) for illumination is also known. 
     Current endoscopes provide limited options to control image characteristics of video images displayed by them. Contrast Limited Adaptive Histogram Equalization (CLAHE) is an image processing algorithm that is used for intensifying the contrast of both luminance and color in image regions depending upon a user defined processing threshold. As a result of the intensification, fine details are enhanced, and thus, may be better detected and diagnosed by a physician. 
     There is a need in the art for image processing methods that may be implemented within the size and hardware limitations of medical devices, such as endoscopes, and which also provide an option to control contrast and/or noise in color and video images and thereby enhance the images. 
     SUMMARY 
     The following embodiments and aspects thereof are described and illustrated in conjunction with systems, tools and methods, which are meant to be exemplary and illustrative, not limiting in scope. The present application discloses numerous embodiments. 
     In some embodiments, the present specification discloses a controller for a multiple viewing elements endoscope system, comprising: a base board module; a field programmable gate array (FPGA) configured to implement a contrast limited adaptive histogram equalization (CLAHE) algorithm to enhance images obtained by said multiple viewing elements system. 
     Optionally, said FPGA comprises an adapter having conversion modules. Still optionally, said FPGA comprises a frame grabber. Optionally, said FPGA comprises a fetching module. Still optionally, said FPGA comprises an interpolation algorithm. Still optionally, said FPGA further comprises a histogram controller. 
     Optionally, said base board module further comprises DDR3 memory in communication with said frame grabber. 
     In some embodiments, the present specification discloses a method of enhancing images obtained by a multiple viewing elements endoscope system using a contrast limited adaptive histogram equalization (CLAHE) algorithm wherein said endoscope system includes a controller having a baseboard module comprising a processor, such as a general processing unit or field programmable gate array (FPGA), configured to implement said algorithm, said method comprising the steps of: inputting YCbCr color space video streams to an adapter on said processor; converting said YCbCr color space video streams to Lab color space video streams within said adapter; pushing said Lab color space video streams to a frame grabber on said processor; grabbing said Lab color space video streams as Lab color space frames within said frame grabber; pulling said Lab color space frames from the frame grabber using a fetching module on said processor; rearranging Lab color space frame data within said fetching module to generate delayed Lab streams; pushing said delayed Lab streams to separate modules within an interpolation algorithm on said processor; and processing said delayed Lab streams with said CLAHE algorithm within said separate modules to generate contrast enhanced Lab streams. 
     Optionally, converting said YCbCr color space streams to Lab color space video streams comprises the steps of: performing YCbCr to RGB conversion using MAD instantiation; 
     performing a function similar to Y(x)=x{circumflex over ( )}2.40 using a LUT; performing RGB to XYZ conversion using MAD instantiation; executing a function similar to Y(x)=x{circumflex over ( )}0.33 using a LUT; 
     and performing XYZ to Lab conversion using MAD instantiation. 
     Optionally, said method further comprises converting said contrast enhanced Lab streams to contrast enhanced YCbCr streams. Still optionally, said converting the contrast enhanced Lab streams to contrast enhanced YCbCr streams comprises the steps of: performing Lab to XYZ conversion using MAD instantiation; executing a function similar to Y(x)=x{circumflex over ( )}0.33 using a LUT; performing XYZ to RGB conversion using MAD instantiation; performing a function similar to Y(x)=x{circumflex over ( )}(1/2.40) using a LUT; and performing RGB to YCbCr conversion using MAD instantiation. 
     In some embodiments, the present specification discloses a method of enhancing images obtained by at least two viewing elements in an endoscope system using a contrast limited adaptive histogram equalization (CLAHE) process wherein said endoscope system includes a controller having a baseboard module comprising a field programmable gate array (FPGA) configured to implement said process, said method comprising the steps of: inputting two YCbCr color space video streams from at the least two viewing elements to an adapter on said FPGA, each viewing element providing one YCbCr color space video stream; converting the at least two YCbCr color space video streams to corresponding at least two Lab color space video streams within said adapter; pushing the at least two Lab color space video streams to a frame grabber on said FPGA; grabbing the at least two Lab color space video streams as corresponding at least two Lab color space frames within said frame grabber; pulling the at least two Lab color space frames from the frame grabber using a fetching module on said FPGA; rearranging Lab color space frame data within said fetching module to generate at least two delayed Lab streams corresponding to the at least two Lab color space frames pulled by the fetching module; pushing the at least two delayed Lab streams to corresponding at least two separate modules within an interpolation algorithm on said FPGA; and processing each delayed Lab stream with said CLAHE algorithm within said separate modules to generate at least two contrast enhanced Lab streams. 
     Optionally, converting a YCbCr color space stream to a Lab color space video stream comprises the steps of: performing YCbCr to RGB conversion using MAD instantiation; 
     performing a function similar to Y(x)=x{circumflex over ( )}2.40 using a LUT; performing RGB to XYZ conversion using MAD instantiation; executing a function similar to Y(x)=x{circumflex over ( )}0.33 using a LUT; and performing XYZ to Lab conversion using MAD instantiation. 
     Optionally, the method of enhancing images obtained by at least two viewing elements further comprises converting each of the at least two contrast enhanced Lab streams to corresponding at least two contrast enhanced YCbCr streams. 
     Optionally, converting each contrast enhanced Lab stream to a contrast enhanced YCbCr stream comprises the steps of: performing Lab to XYZ conversion using MAD instantiation; executing a function similar to Y(x)=x{circumflex over ( )}0.33 using a LUT; performing XYZ to RGB conversion using MAD instantiation; performing a function similar to Y(x)=x{circumflex over ( )}(1/2.40) using a LUT; and performing RGB to YCbCr conversion using MAD instantiation. 
     Optionally the method of enhancing images wherein the images are obtained from three viewing elements comprises the steps of: inputting three YCbCr color space video streams from the three viewing elements to an adapter on said FPGA; converting the three YCbCr color space video streams to corresponding three Lab color space video streams within said adapter; pushing the three Lab color space video streams to a frame grabber on said FPGA in form of a video stream obtained from a single viewing element, a Y input of the frame grabber being fed by a first viewing element&#39;s Lab color space video stream, a Cb input of the frame grabber being fed by a second viewing element&#39;s Lab color space video stream, and a Cr input of the frame grabber being fed by a third viewing element&#39;s Lab color space video stream; grabbing the three Lab color space video streams as corresponding three Lab color space frames within said frame grabber; pulling the three Lab color space frames from the frame grabber using a fetching module on said FPGA; rearranging Lab color space frame data of the three Lab color space frames within said fetching module to generate three delayed Lab streams corresponding to the three Lab color space frames pulled by the fetching module; pushing the three delayed Lab streams to corresponding three separate modules within an interpolation algorithm on said 
     FPGA; and processing each delayed Lab stream with said CLAHE algorithm within said separate modules to generate three contrast enhanced Lab streams being a first, a second and a third contrast enhanced Lab stream, each contrast enhanced Lab stream corresponding to a viewing element of the endoscope. 
     Optionally, the first viewing element is a left viewing element of the endoscope, the second viewing element is a central viewing element of the endoscope, and the third viewing element is a right viewing element of the endoscope. 
     Optionally, the first of the three contrast enhanced Lab streams is displayed as a first image on one or more display screens coupled with the controller, the second of the three contrast enhanced Lab streams is displayed as a second image on one or more display screens coupled with the controller, and the third of the three contrast enhanced Lab streams is displayed as a third image on one or more display screens coupled with the controller. 
     Optionally, each contrast enhanced Lab stream is displayed as a contrast enhanced image on a display device coupled with the controller, each contrast enhanced image comprising a plurality of frames having a higher degree of contrast as compared to the corresponding plurality of frames in the corresponding image obtained from a viewing element of the endoscope before being processed using the image enhancement method of the present specification. 
     The aforementioned and other embodiments of the present specification shall be described in greater depth in the drawings and detailed description provided below. 
    
    
     
       BRIEF DESCRIPTION OF THE DRAWINGS 
       These and other features and advantages of the present invention will be appreciated, as they become better understood by reference to the following detailed description when considered in connection with the accompanying drawings, wherein: 
         FIG. 1  illustrates a multiple camera endoscopy system, according to some embodiments of the present specification; 
         FIG. 2  schematically depicts an exemplary layout of an endoscopy system and an interface unit deployed in an operating room, according to an embodiment of the present specification; 
         FIG. 3  is a block diagram illustrating an exemplary video processing architecture, according to an embodiment of the present specification; 
         FIG. 4A  illustrates components of a field programmable gate array (FPGA) and its periphery, according to an embodiment of the present specification; 
         FIG. 4B  illustrates derivation of a cumulative distribution function (CDF) achieved by clipping a histogram using a low threshold, according to an embodiment of the present specification; 
         FIG. 4C  illustrates derivation of a CDF achieved by clipping a histogram, using a higher threshold than shown in  FIG. 4B , according to an embodiment of the present specification; 
         FIG. 5A  is a flowchart illustrating the steps of enhancing images obtained by a multiple viewing elements endoscope system using a contrast limited adaptive histogram equalization (CLAHE) algorithm, in accordance with an embodiment of the present specification; 
         FIG. 5B  is a flowchart illustrating the steps of enhancing images obtained by an endoscope system having three viewing elements, by using a contrast limited adaptive histogram equalization (CLAHE) algorithm, in accordance with an embodiment of the present specification; 
         FIG. 6A  illustrates a process pipeline that converts YCbCr color space to Lab color space, in accordance with embodiments of the specification; 
         FIG. 6B  is a flowchart illustrating the steps performed by the process pipeline shown in  FIG. 6A ; 
         FIG. 7A  illustrates a process pipeline that converts Lab color space to YCbCr color space, in accordance with embodiments of the specification; 
         FIG. 7B  is a flowchart illustrating the steps performed by the process pipeline shown in  FIG. 7A ; 
         FIG. 8A  illustrates a traditional image captured by an endoscope placed inside a body cavity; and 
         FIG. 8B  illustrates the image of  FIG. 8A  enhanced by using the method of the present specification. 
     
    
    
     DETAILED DESCRIPTION 
     The present specification discloses systems and methods for enhancing images by using a contrast limited adaptive histogram equalization (CLAHE) algorithm in a processor, such as a field programmable gate array (FPGA). The images may be obtained by the imaging elements of a multiple imaging elements endoscope of an endoscopy system. 
     The present specification is directed towards multiple embodiments. The following disclosure is provided in order to enable a person having ordinary skill in the art to practice the invention. Language used in this specification should not be interpreted as a general disavowal of any one specific embodiment or used to limit the claims beyond the meaning of the terms used therein. The general principles defined herein may be applied to other embodiments and applications without departing from the spirit and scope of the invention. Also, the terminology and phraseology used is for the purpose of describing exemplary embodiments and should not be considered limiting. Thus, the present invention is to be accorded the widest scope encompassing numerous alternatives, modifications and equivalents consistent with the principles and features disclosed. For purpose of clarity, details relating to technical material that is known in the technical fields related to the invention have not been described in detail so as not to unnecessarily obscure the present invention. In the description and claims of the application, each of the words “comprise” “include” and “have”, and forms thereof, are not necessarily limited to members in a list with which the words may be associated. 
     As used herein, the indefinite articles “a” and “an” mean “at least one” or “one or more” unless the context clearly dictates otherwise. 
     It should be noted herein that any feature or component described in association with a specific embodiment may be used and implemented with any other embodiment unless clearly indicated otherwise. 
     Embodiments of methods and/or devices of the specification may involve performing or completing selected tasks manually, automatically, or a combination thereof. Some embodiments of the specification are implemented with the use of components that comprise hardware, software, firmware or combinations thereof. In some embodiments, some components are general-purpose components such as general purpose computers or oscilloscopes. In some embodiments, some components are dedicated or custom components such as circuits, integrated circuits or software. 
     For example, in some embodiments, at least a portion of the methods may be implemented as a plurality of software instructions executed by a data processor, which may be part of a general-purpose or custom computer. In some embodiments, the data processor or computer comprises volatile memory for storing instructions and/or data and/or a non-volatile storage, for example, a magnetic hard-disk and/or removable media, for storing instructions and/or data. In some embodiments, implementation includes a network connection. In some embodiments, implementation includes a user interface, generally comprising one or more input devices (e.g., allowing input of commands and/or parameters) and output devices (e.g., allowing reporting parameters of operation and results). 
     It is appreciated that certain features of the specification, which are, for clarity, described in the context of separate embodiments, may also be provided in combination in a single embodiment. Conversely, various features of the specification, which are, for brevity, described in the context of a single embodiment, may also be provided separately or in any suitable sub-combination or as suitable in any other described embodiment of the specification. Certain features described in the context of various embodiments are not to be considered essential features of those embodiments, unless the embodiment is inoperative without those elements. 
     It is noted that the term “endoscope” as mentioned to herein may refer particularly to a colonoscope, according to some embodiments, but is not limited only to colonoscopes. The term “endoscope” may refer to any instrument used to examine the interior of a hollow organ or cavity of the body. 
     It should also be noted that a plurality of terms, as follows, appearing in this specification are used interchangeably to apply or refer to similar components and should in no way be construed as limiting:
         “Utility tube/cable” may also be referred to as an “umbilical tube/cable”   A “main control unit” may also be referred to as a “controller unit”, “main controller” or “fuse box”.   A “viewing element” may also be referred to as an image capturing device/component, viewing components, camera, TV camera or video camera.   A “working channel” may also be referred to as a “service channel”.   An “illuminator” may also be referred to as an “illumination source”, and in some embodiments, an LED.   A “flexible shaft” may also be referred to as a bending section or vertebra mechanism.   A “video stream” refers to a series of individual frames. It should be appreciated that, when the methods and systems of the present embodiment are applied to a video stream, they are applied to each individual frame, on a frame-by-frame, or group of frames, basis.       

     Further, as used in this specification, the term “camera” is used to describe a device for capturing light. Thus, a camera, in some embodiments, comprises at least one optical lens assembly. In some embodiments, the term “camera′ is used to describe an optical lens assembly and its associated image sensor. In some embodiments, the term “camera” is used to describe an optical imaging system, such as a lens assembly or assemblies and associated solid state detector arrays. In some embodiments, the terms “viewing element” and “camera” may be used interchangeably. 
     As used in the specification, the term “optical assembly” is used to describe a set of components that allows the endoscopic device to capture light and transform that light into at least one image. In some embodiments, lenses/optical elements are employed to capture light and image capturing devices, such as sensors, are employed to transform that light into at least one image. 
     Image capturing devices may be Charged Coupled Devices (CCD&#39;s) or Complementary Metal Oxide Semiconductor (CMOS) image sensors, or other suitable devices having a light sensitive surface usable for capturing an image. In some embodiments, a sensor such as a Charge Coupled Device (CCD) or a Complementary Metal Oxide Semiconductor (CMOS) image sensor (for detecting the reflected light received by an optical element), is employed. 
     In some embodiments, an optical element comprises a plurality of optics such as lens assemblies, lenses and protective glass, and is configured to receive reflected light from target objects. 
     An optical assembly, as used in the specification, comprises at least one lens assembly, its associated sensor(s), and its associated circuit board. In some embodiments, an “optical assembly” may comprise more than one viewing element or camera, associated sensor(s), and associated circuit board(s). In some embodiments, an “optical assembly” may comprise a front viewing element, its associated sensor, and its associated circuit board. In some embodiments, an “optical assembly” may comprise a front viewing element, its associated sensors, and its associated circuit board and/or at least one side viewing element, its associated sensors and its associated circuit boards. Further, the optical assembly typically is associated with at least one illuminator for illuminating the field of view. Thus, for example, a front-pointing optical assembly includes a front-pointing viewing element with associated sensor, associated circuit board and is associated with at least one illuminator. 
     Endoscopes that are currently being used typically have a front and side viewing elements for viewing the internal organs, illuminators, a fluid injector for cleaning the lens of the viewing elements, and sometimes also illuminators and a working channel for insertion of surgical tools. The illuminators commonly used are fiber optics that transmit light, generated remotely, to the endoscope tip section. The use of light-emitting diodes (LEDs) for illumination is also known. 
     A tip section of the endoscope assembly may be inserted into a patient&#39;s body through a natural body orifice, such as the mouth, nose, urethra, vagina, or anus. 
     In accordance with an embodiment of the present specification, a tip cover may house the tip section. The tip section, with the tip cover, may be turned or maneuvered by way of a flexible shaft, which may also be referred to as a bending section, for example, a vertebra mechanism. Tip cover may be configured to fit over the inner parts of the tip section, including an electronic circuit board assembly and a fluid channeling component, and to provide protection to the internal components in the inner parts, such as a body cavity. The endoscope can then perform diagnostic or surgical procedures inside the body cavity. The tip section carries one or more viewing elements, such as cameras, to view areas inside body cavities that are the target of these procedures. 
     Tip cover may include panels having a transparent surface, window or opening for optical lens assemblies of viewing elements. The panels and viewing elements may be located at the front and sides of the tip section. Optical lens assemblies may include a plurality of lenses, static or movable, providing different fields of view. 
     An electronic circuit board assembly may be configured to carry the viewing elements, which may view through openings on the panels. Viewing elements may include an image sensor, such as but not limited to a Charge Coupled Device (CCD) or a Complementary Metal Oxide Semiconductor (CMOS) image sensor. 
     The electronic circuit board assembly may be configured to carry illuminators that are able to provide illumination through illuminator optical windows. The illuminators may be associated with viewing elements, and may be positioned to illuminate the viewing elements&#39; fields of view. 
     One or more illuminators may illuminate the viewing fields of the viewing elements. In an embodiment, the illuminators may be fiber optic illuminators that carry light from remote sources. The optical fibers are light carriers that carry light from a remotely located light source to the illuminators. The optical fibers extend along an insertion tube between the tip section at a distal end of the endoscope, and a handle at a proximal end. An umbilical/utility tube connects the handle to a main control unit. The main control unit enables control of several functions of the endoscope assembly, including power delivered and communication of signals between the endoscope and its display, among others. 
     Reference is now made to  FIG. 1 , which shows a multi-viewing elements endoscopy system  100 . System  100  may include a multi-viewing elements endoscope  102 . Multi-viewing elements endoscope  102  may include a handle  104 , from which an elongated shaft  106  emerges. Elongated shaft  106  terminates with a tip section  108  which is turnable by way of a bending section  110 . Handle  104  may be used for maneuvering elongated shaft  106  within a body cavity. The handle may include one or more buttons and/or knobs and/or switches  105  which control bending section  110  as well as functions such as fluid injection and suction. Handle  104  may further include at least one, and in some embodiments, one or more working channel openings  112  through which surgical tools may be inserted as well as one and more side service channel openings. 
     A utility cable  114 , also referred to as an umbilical tube, may connect between handle  104  and a Main Control Unit  199 . Utility cable  114  may include therein one or more fluid channels and one or more electrical channels. The electrical channel(s) may include at least one data cable for receiving video signals from the front and side-pointing viewing elements, as well as at least one power cable for providing electrical power to the viewing elements and to the discrete illuminators. 
     The main control unit  199  contains the controls required for displaying the images of internal organs captured by the endoscope  102 . The main control unit  199  may govern power transmission to the endoscope&#39;s  102  tip section  108 , such as for the tip section&#39;s viewing elements and illuminators. The main control unit  199  may further control one or more fluid, liquid and/or suction pump(s) which supply corresponding functionalities to the endoscope  102 . One or more input devices  118 , such as a keyboard, a touch screen and the like may be connected to the main control unit  199  for the purpose of human interaction with the main control unit  199 . In the embodiment shown in  FIG. 1 , the main control unit  199  comprises a screen/display  120  for displaying operation information concerning an endoscopy procedure when the endoscope  102  is in use. The screen  120  may be configured to display images and/or video streams received from the viewing elements of the multi-viewing element endoscope  102 . The screen  120  may further be operative to display a user interface for allowing a human operator to set various features of the endoscopy system. 
     Optionally, the video streams received from the different viewing elements of the multi-viewing element endoscope  102  may be displayed separately on at least one monitor (not seen) by uploading information from the main control unit  199 , either side-by-side or interchangeably (namely, the operator may switch between views from the different viewing elements manually). Alternatively, these video streams may be processed by the main control unit  199  to combine them into a single, panoramic video frame, based on an overlap between fields of view of the viewing elements. In an embodiment, two or more displays may be connected to the main control unit  199 , each for displaying a video stream from a different viewing element of the multi-viewing element endoscope  102 . The main control unit  199  is described in U.S. patent application Ser. No. 14/263,896, entitled “Video Processing in a Compact Multi-Viewing Element Endoscope System” and filed on Apr. 28, 2014, which is herein incorporated by reference in its entirety. 
       FIG. 2  schematically depicts a layout of an endoscope system  210  and an associated interface unit  2900  deployed in an operating room, according to some embodiments. A patient  280  is supported on a bed  282  and a physician  284  may employ an endoscope  220  of endoscope system  210  in an endoscopic procedure. An assistant  286  assists physician  284  on the other side of bed  282  across from physician  284 . 
     Endoscope  220  is connected to a main controller  230  by a utility cable  232 . In embodiments, endoscope  220  provides three simultaneous endoscopic views using three cameras housed in the tip of endoscope  220 . Main controller  230  is connected to three display screens,  240   a ,  240   b , and  240   c , wherein each display screen may be configured to display a corresponding view of the three endoscopic views provided by endoscope system  210 , substantially as described above. Display screens  240   a ,  240   b , and  240   c  are positioned facing physician  284  and possibly elevated so that physician  284  may conduct the endoscopic procedure by looking at the screen displays and having an undisturbed line of site thereto. In some embodiments, display screens  240   a ,  240   b , and  240   c  are in the form of a single large screen. 
     Interface unit  2900  comprises an image processor encased with main controller  230 , and an interface unit display  2920  functionally associated with the image processor. The image processor simultaneously receives image data associated with the three views provided by endoscope  220  from three respective imaging channels and generates images comprising image data from the three views, wherein the images are displayable on interface unit display  2920 . For example, the three cameras of endoscope  220  may provide three incoming video streams, respectively, and the image processor may then generate a single video stream comprising image data from the three incoming video streams, substantially as described above. 
     According to some embodiments, interface unit display  2920  is functionally associated with the image processor encased with main controller  230  by a cable. In some embodiments, interface unit display  2920  is wirelessly associated with the image processor. According to some embodiments, interface unit display  2920  is substantially portable and may be deployed in a multitude of positions within the operating room. Moreover, according to some embodiments, interface unit display  2920  may be easily displaced from position to position within the operating room during a procedure. For example, interface unit display  2920   b  or  2920   c  may be positioned so that both physician  284  and assistant  286  can watch the screen thereof, or interface unit display  2920   a  may be positioned facing assistant  286 . 
     In some embodiments, interface unit  2900  comprises an interface unit computer, functionally associated with main controller  230  and with the image processor encased therewith. 
     In some embodiments, interface unit  2900  comprises a user interface module  2922  associated with interface unit display  2920 , and assistant  286  may employ user interface module  2922  to command interface unit  2900  and/or interface unit computer, and/or endoscope system  210 . For example, assistant  286  may employ user interface module  2922  to input and store, in the interface unit computer, patient-related textual information, such as relevant biographical data, before or during an endoscopic procedure. According to some embodiments, user interface module  2922  comprises a touch screen  2924 . 
     According to some embodiments, interface unit computer may communicate with a computer network, substantially as described above and using an access point  290  installed in the operating room and allowing access to such a computer network. Access point  290  may comprise a LAN connector to which the interface unit computer is connected through a LAN cable. According to some embodiments, access point  290  may be a Wi-Fi modem with which the interface unit computer may communicate wirelessly. 
       FIG. 3  is a circuit/component diagram detailing the operative connection between a video controller or a controller circuit board  320  of the main control unit  199  of  FIG. 1  and endoscope  310  and display units  350 . Referring to  FIG. 3 , video controller/controller circuit board  320  comprises a camera board  321  that controls the power supplies to LEDs  311 , transmits controls for the operation of image sensor(s)  312  (corresponding to one or more cameras) in the endoscope, and converts pre-video signals  313  from image sensors  312  to standard video signals. Image sensor(s)  312  may be charge coupled devices (CCD) or complementary metal oxide semiconductor (CMOS) imagers. Camera board  321  receives pre-video signal(s)  313  generated by the CCD imagers and also other remote commands  314  from the endoscope  310 . 
     The controller circuit board  320  further comprises elements for processing video obtained from image sensors  312  through camera board  321 , as well as other elements for system monitoring and control. All these elements are connected with a Base Board Module  352 , which is a printed circuit board (PCB). In various embodiments, some of these elements are integrated circuits (ICs) that are connected by soldering, an element  326  (SOM or System on Module) is connected by mounting, while all other elements are connected by means of cables. 
     Various elements connected with the Base Board Module  352  are described as follows: 
     FPGA (Field Programmable Gate Array)  323 : 
     An FPGA  323  is a programmable logic device that may be customized for the system requirements and performs tasks that may be categorized by two types: logic tasks which are preferably implemented by hardware (as opposed to software), and logic tasks related to video image processing. In one embodiment, Base Board Module  352  may include one or more double data rate type three synchronous dynamic random access memory modules (DDR3)  333  in communication with FPGA  323 . 
     Logic tasks that are preferably implemented by hardware may include, but are not limited to: 
     1. Initializing some Base Board Module&#39;s  352  ICs upon system power-up;
 
2. Monitoring buttons  340  for White Balance, LED on/off, Air Flow, and Power on/off on front-panel  335 ;
 
3. Monitoring SOM&#39;s  326  proper operation using a watch-dog mechanism;
 
4. Backing-up some of the system&#39;s parameters (example: airflow level), even while the system is switched off; and
 
5. Communicating with Camera Board  321 .
 
     Logic tasks related to video image processing (that may have software-configurable parameters) include, and may not be limited to: 
     1. Multiplexing video inputs—Each of the multiple imaging elements has several video interfaces that are multiplexed via a Video Input Interface  351 . Further, in some embodiments, several auxiliaries are multiplexed via an Auxiliary Video Input Interface  325 .
 
2. Internal test pattern to video outputs via Video Output Interface  324  to multiple displays.
 
3. Conversion between cameras&#39; video standard to display video standard.
 
4. OSD (On Screen Display) insertion, also known as graphic overlay.
 
     5. PIP (Picture-in-Picture). 
     6. Stitching images from several cameras into one image displayed on a single screen.
 
7. Image adjustments, such as brightness, contrast, etc.
 
     Auxiliary Video Input Interface  325 : 
     In one optional embodiment, the video input to Auxiliary Video Input Interface  325  may comprise analog video, such as in color, video, blanking, sync (CVBS), S-Video or YPBPR format or digital video (DVI), and may be displayed as such. 
     SOM (System on Module)  326 : 
     The SOM  326  may provide an interface to input devices such as keyboard, mouse, and touchscreen via Touch I/F  327 . Through these input devices, together with buttons  340  in Front Panel  335 , the user may control the system&#39;s functionality and operational parameters. In one embodiment, a peripheral component interconnect express (PCIe) bus connects SOM  326  with FPGA  323 . Types of data traffic over the PCIe may include: 
     a. SOM  326  to FPGA  323 : Commands (for example, when the user changes operational parameters); and
 
b. FPGA  323  to SOM  326 : Registers values, which provide an indication of the internal status, and captured images.
 
     Other Functionalities: 
     Controller circuit board  320  may further control one or more fluid, liquid and/or suction pump(s) which supply corresponding functionalities to the endoscope through a pneumatic I/F  328 , a pump  329  and a check valve  330 . Controller circuit board  320  may further comprise an on-board power supply  345  and a front panel  335  that may provide operational buttons  340  for the user. 
     Camera board  321  may receive video signal(s)  313  which, in one embodiment, comprises three video feeds, corresponding to video pickups by three endoscopic tip viewing elements (one front and two side-looking viewing elements), as generated by the corresponding image sensor(s)  312 . In one embodiment, the three video feed pickups, corresponding to the three viewing elements (the front-looking, left-side looking and right-side looking viewing elements) of an endoscopic tip, are displayed on three respective monitors. 
     As discussed above, FPGA  323  includes logic modules for various purposes, in accordance with embodiments of the specification. In some embodiments, FPGA  323  implements a contrast limited adaptive histogram equalization (CLAHE) algorithm in order to enhance imaging. CLAHE is an image processing algorithm to intensify the contrast of both luminance and color in image regions where differences between neighboring pixels are small. As a result, fine details are enhanced that may be better detected and diagnosed by a physician. In embodiments, an endoscope using CLAHE may provide enhanced images of polyps or blood vessels on an intestine wall. In embodiments, these images are real-time video images captured by one or more cameras of the endoscope. 
       FIG. 4A  illustrates components of an FPGA  402 , which may be similar to FPGA  323  of  FIG. 3 , in accordance with some embodiments of the present specification.  FIG. 4A  also illustrates a DDR3 memory device  470  in communication with FPGA  402 . In some embodiments, FPGA  402  and DDR3 memory device  470  are located in a base board module  401  within an endoscope system. In embodiments, FPGA  402  receives images captured by all viewing elements in the endoscope system. In alternative embodiments, each viewing element may be in communication with a FPGA, similar to FPGA  402 . 
     In some embodiments, YCbCr input  403  from each viewing element is input through pipelines  404  to an adapter  405 . In some embodiments, each YCbCr input is 8 bit, 10 bit, or of any other length per component. In one embodiment, the YCbCr input for adapter  405  are of 10 bit per component. The adapter  405  includes “Lab,  10   b ” modules  406 . The adapter  405  converts YCbCr input  403  used as a part of the color image pipeline to a Lab color space, in accordance with some embodiments. A “Lab” color space is a color space with dimension  1 ′ for lightness and ‘a’ and ‘b’ for the color-opponent dimensions, based on nonlinearly compressed coordinates. The Lab color space includes all perceivable colors. Lab color space is designed to be perceptually uniform, and allows correlation of image contrast enhancement of an algorithm used herein and described subsequently, with its perceptual quality. A bitmap image represented as Lab requires more data per pixel to obtain the same precision as its counterpart YCbCr bitmap. In some embodiments, each YCbCr input  403  including 10 bit per color component is converted by the adapter  405  to a 12 bit per component Lab color space video stream, of which all 12 bits are used for the L component, whereas 10 bits are used for each of a and b color components, totaling 32 bits per Lab pixel. 
     The video stream, i.e. set of frames, generated by the adapter  405  may be driven to two different destinations, and thus may have at least two purposes. The first purpose is, in some embodiments, to drive a delay line comprising on-board DDR3  470  and an FPGA-internal frame grabber  450 . In some embodiments, one frame delay (if video is progressive, when interlaced, as is the case with current NTSC sensors where the delay is one video field) may be introduced through the delay line. In alternative embodiments, the delay line may be implemented as an FPGA-internal memory. As mentioned above, DDR3  470  delay line path, fed from adapter  405 , uses 12 bits for L component and 10 bits for each of a and b components (32 bit in total for one Lab pixel). In some embodiments, DDR3  470  supports eight banks per memory, of which two banks are used for the frame delay line. 
     In some embodiments, the FPGA  402  comprises a single FPGA-internal frame grabber  450 , common to all viewing elements. It should be appreciated that the FPGA  402 , in some embodiments, comprises a plurality of FPGA-internal frame grabbers, similar to the frame grabber  450 . In some embodiments, there are at least three FPGA-internal frame grabbers, one corresponding to each of the three viewing elements or cameras of the endoscope. Also, each of the plurality of frame grabbers has an onboard DDR3 memory (similar to the DDR3  470 ). Thus, base board  401  includes a plurality of DDR3 memory components associated with the plurality of frame grabbers. In still further embodiments, use of the on-board DDR3 memory, for the delay line, is optional in order to reduce latency and spare hardware. 
     In embodiments, frame grabber  450  is fed with three video streams (one per viewing element), each comprising a Lab color space. Individual frames from the streams are converted by adapter  405  to form compatible digital video streams. One of the functions implemented by adapter  405  is to make the video stream feeding the frame grabber  450  appear as if it is input from a single viewing element, and not multiple viewing elements (such as the three viewing elements used for the purpose of this description). In some embodiments, frame grabber&#39;s  450  Y input is fed by a left viewing element&#39;s Lab, Cb input by a central viewing element&#39;s Lab, and Cr input by a right viewing element&#39;s Lab, meaning that frame grabber  450  is fed by three viewing elements. This mode of operation may be advantageous in using a single frame grabber (for use with one camera endoscopes in accordance with some embodiments) with a multiple camera endoscope. 
     In some embodiments, Lab color space frames, corresponding to the three viewing elements, are fetched from the frame grabber  450  by a fetching module  460 . The fetching module  460  may keep track of the ingress video frame timing (for example, line count). In embodiments, fetching module  460  may instruct frame grabber  450  on which rows to fetch from DDR3  470 . These rows are calculated from the video lines that may be needed to be displayed, and which are at constant phase shift relative to the ingress frame. Fetching module  460  also rearranges the data from fetched rows to a format understood by an interpolation algorithm  420 . The data from the fetched rows may include three video streams (one per each viewing element) where each video stream comprises Lab components. The delayed Lab streams, corresponding to each viewing element, are fed to separate modules within interpolation algorithm  420  where they are similarly processed in accordance with the CLAHE algorithm of the present specification. 
     As discussed, the video stream generated by the adapter  405  may be driven to two different destinations, and thus may have at least two purposes. For the second purpose, a second path output from the adapter  405  uses 6 bit per each Lab component to send to elements  410  that build and store histogram information in accordance with various embodiments of the present specification. The image information output from adapter  405  may be perceived to be split into several tiles by elements  410 . Units of the tile heights are in video lines and the tile widths are in pixels. Tiles may be described by attributes, such as key vertical coordinates including start, center, and end. In embodiments, each tile overlaps with its neighboring tiles. Overlapping may reduce the tiling or bordering effect. As understood by those skilled in the art, a result of the tiling effect is that an image may appear to contain vertical and/or horizontal line(s) going through the tile centers. The vertical/horizontal lines may appear to divide the image into distinct rectangular regions, corresponding to the tiles. The rectangular regions may differ in their luminance and/or chrominance. 
     In embodiments, overlapping tiles to the maximum (50% theoretical—approximately 48% in practice—on each side, per axis) may mitigate the tiling effect to a reasonable extent. In addition, using bi-cubic instead of bi-linear interpolation for inter-tile interpolation, may further reduce the tiling effect. It should be appreciated, that the higher the percentage overlap, the better is the reduction or mitigation of the tiling effect. At the same time, reducing the percentage overlap may increase the level of local enhancement of the image since the tiles can become smaller. Independently, both the locality of enhancement of the image and tiling effect improve as number of tiles increases. In some embodiments, 64 tiles are used/arranged as an 8×8 array, that is, an 8 vertical×8 horizontal tile structure. 
     Latency is necessary in any real-time CLAHE implementation, regardless of the type of platform running the algorithm. Practical latency is between 30% to 100% frame—meaning it is unnoticeable to the human eye (under normal circumstances of 24 frames per seconds or higher), provided the accumulative latency due to other elements in the system does not reach a critical limit. The CLAHE latency is caused due to the fact that before the interpolation algorithm  420  can fetch CDF (Cumulative Distribution Function) values from a pair (pair, due to the bilinear interpolation in some embodiments) of histogram (tile) rows, sufficient time must be allowed for all the pixels covered by said two rows of tiles to flow into the FPGA  402  and build the relevant histograms. With the more preferable bi-cubic inter-tile interpolation, in various embodiments, yet longer latency is required as instead of two rows, four rows need be fetched. Also, the step of transforming a histogram to a CDF by clipping, integration and normalization (as well as other processes) adds more latency. For example, if there are four histogram (tiles) rows, and a pair of rows is needed for interpolation, the order of magnitude of latency will approach 50% frame. A preferred practical latency would be 100% frame (if video is progressive) or 100% field (if video is interlaced)—this is because gamut fitting (i.e. minimization of out-of-gamut problem) requires first grabbing an entire frame (or field) to extract its ingress (I) and enhanced (E) statistics (min, average., max) as part of building the CDF functions. It should be noted that a 100% delay also covers the case of fetching of four tile rows as is required by the bi-cubic interpolation. 
     Per ingress video line, specific actions are performed by the CLAHE algorithm. For example, at a row 0, video lines covered by the tiles of row 0 are 0-70. Therefore, sometime before the start of these lines (line 238, for example, the end of previous frame), the histograms are reset. In lines 0-70, the histograms are being built, therefore immediately afterwards, to reduce latency, lines 71-75 (76-79 are safety margins or spare) convert the histograms to CDFs. To support the case where row 0 participates in a bilinear interpolation (together with a row 1), only after row 1 finishes its own CDF generation (at ingress line 135), can the first video line participating in the row 0+1 interpolation be fetched and transmitted to the screen (line 36-center of row 0). This example also demonstrates the CLAHE latency: when line 36 is transmitted to the screen (or next pipeline stage), the ingress video line is already 136, hence latency is (136−36)/240=42% of a frame (in actual, an NTSC field). However, this example applies only in the embodiments where bi-linear inter-tile interpolation is used, and, gamut fitting is not required. 
     Three histograms may be allocated for each tile, such that each histogram corresponds to a color component (L/a/b). The histograms may form distribution functions of the Lab values related with the ingress pixels that are covered by the tile.  FIG. 4A  illustrates a group of memory elements incorporated into elements  410  that correspond to one viewing element. Elements  410  may describe 384 histograms (1 [viewing element]×3[color components of lab]×8[rows of histograms]×8[histograms per row]×2[buffers]). The two buffers are needed in the case of 100% delay which necessitates that one buffer of histograms collect the ingress video and get built, while the other buffer hold the histograms of the previous frame and is converted to an array of CDFs. In the next ingress video frame, the buffers swap roles. This technique is called double-buffering. In another embodiment where double-buffering is not implemented, elements  410  may describe 72 histograms (3 components×4 rows×6 tiles=72). Similarly, in yet another embodiment, elements  410  may describe 192 histograms (3 components×8 rows×8 tiles=192). 
     In some embodiments, each histogram is based on one FPGA-internal 9K-bit memory module providing 512 bins of 18 bit each. In alternative embodiments, the numbers of histograms may vary, for example the number could be 8×8 histograms per color component. In alternative embodiments, to reach high FPGA utilization efficiency, number of bins per histograms (and, CDF) may be reduced from 512 to, for example, 64 with said one 9K-bit memory module supporting 8 histograms instead of 1. In the embodiments of 64 bin CDF representation, the FPGA uses bi-linear interpolation between two adjacent CDF bins, to improve accuracy to a level comparable with that of higher order CDFs (256 bins, 512 bins etc.). 
     In embodiments, a threshold may be set by a user, for the histogram bins. In embodiments, the threshold is given by the user through a SOM-run GUI aided with an input interface (keyboard, mouse, touchscreen). In embodiments, upon physician&#39;s disconnecting the endoscope and system folding back to displaying a pattern generator, the user-defined thresholds are automatically bypassed by the FPGA  402  to be 0, so the pattern generator&#39;s appearance will seem natural to the user (threshold of 0 is equivalent to CLAHE deactivation). Once an endoscope is connected again, the bypass is cancelled; hence original user-defined thresholds are restored. An alternate means of bypassing comprises usage of the original Lab pixels at the output of the delay lines as the output of the CLAHE, without replacing them with the CDF values—hence the CDFs are bypassed altogether. The bins may be clipped beyond the set threshold level. Additionally, excess samples after clipping may be equally distributed over all the histogram&#39;s bins. As a result, the user may be able to control contrast and/or noise of an image that is subsequently displayed. 
     It should be appreciated that the user-defined thresholds are preferably determined by a user based upon what he or she considers to be a pleasant contrast. The theoretical threshold range is [0,1], where zero means no enhancement at all, or deactivation of the CLAHE process, and one means maximum enhancement, which is the maximum color enhancement of CLAHE that is equal to the maximum of CDF bins difference in the tile plus the interpolation. The maximum value can be normalized to other ranges as well according to the bit depth of the image and the tile size. 
       FIG. 4B  illustrates derivation of a CDF by clipping a histogram, using a low threshold, in accordance with an embodiment of the present specification. As shown histogram  4002  is clipped to firstly obtain an intermediary chart  4004  which upon computation results in CDF  4008 . Due to application of a lower threshold during clipping, the resulting CDF  4008  resembles an identity function (straight line, constant slope).  FIG. 4C  illustrates derivation of a CDF by clipping a histogram, using a higher threshold, in accordance with an embodiment of the present specification. As shown histogram  4010  is clipped to firstly obtain an intermediary chart  4012  which upon computation results in CDF  4014 . Due to the application of a higher threshold during clipping, the resulting CDF  4014  has a steep slope in the region where the histogram peaks, whereas in other regions, the slope is moderate. In embodiments, a clipping threshold level is determined empirically, and may be based on a physician&#39;s preference. For a given measure of contrast enhancement, clipping threshold may be lowered as number of histograms (per color component) increase. This is caused because increasing number of histograms for the same resolution results in fewer pixels covered by a histogram. Inversely, clipping threshold may be increased as image resolution increases for the same number of tiles. This is caused because there are now more pixels covered by a histogram. It should be noted that in some embodiments, the clipping threshold can be set per a specific color component (L/a/b) of a specific camera (left, front, right) of the endoscopes. This is useful, for example, in cases where side cameras (left and right side viewing cameras) may have different CLAHE requirements from the front camera, or where the luminance (L) may have different CLAHE requirements from the color (a, b). 
     The modified histograms, with optionally controlled contrast and noise, may be converted into Cumulative Distribution Functions (CDFs) and normalized, so that CDF bin content corresponding to a highest bin number may represent full-scale value of an L, a, or b component. The resulting normalized CDFs may be used as Look-Up Tables (LUTs) whose input may be the L, a, and b pixel values. Output of the LUTs may be corresponding L, a, and b pixel values of modified contrast. 
     Referring back to  FIG. 4A , output of elements  410  and 10 bit delayed Lab stream  425  may simultaneously be fed to interpolation algorithm module  420 . Stream  425  provides information related to the original Lab values of the ingress pixels to interpolation algorithm module  420 . The information is provided on a per-pixel basis. Module  420  may utilize the Lab values as input corresponding to relevant histograms, which may be in the form of CDFs as explained above. In embodiments, module  420  may interpolate from a minimal case of four up to a maximal case of thirty two (32) CDFs per color component per camera to obtain a final single contrast-enhanced Lab pixel. The former, minimal case, applies where inter-tile interpolation is bi-linear, and, CDFs are wide (i.e.  256 ,  512 , or even more). The latter, maximal case, applies where inter-tile interpolation is bi-cubic and each of 16 CDFs is in itself a bi-linear interpolation of two adjacent narrow (64 bin) CDFs. For each output Lab pixel, four or sixteen respective tiles may be selected. The Lab pixel may reside in a rectangle formed by center points of the selected four (or sixteen) tiles. In embodiments, the pixel&#39;s Lab values feed the LUTs of its respective four (or sixteen) tiles. The final Lab values of the output pixel may be a bi-linear interpolation of the four sets of Lab values (or bi-cubic interpolation of the sixteen sets of Lab values). Thus, module  420  may utilize the Lab values to apply the interpolation algorithm in order to generate contrast-enhanced Lab values, in accordance with the embodiments discussed above. Contrast enhanced Lab pixels are fed to modules  430  that convert them to contrast enhanced YCbCr 4:2:2 10 bit video outputs  440 . 
     Referring again to  FIG. 4A , modules  430  may be implemented with successive steps of matrix multiplication and vector addition (MAD) and non-linear functions (implemented as Look-Up Tables, i.e. LUTs). Outputs  440  may subsequently be fed to the next stages of the video pipeline. Formatting output  440  to YCbCr 4:2:2 10 bit may maintain the compatibility between the existing modules within FPGA  402  and may reduce design efforts. 
     In embodiments, each component within FPGA  402  may include a combination of one or more of the following elements whose properties may vary depending on the FPGA vendor and FPGA family:
     1. Look Up Tables (LUTs) for combinational functions. Per such a LUT: 1 bit output as a function of 4-6 bit input.   2. Flip-Flops for sequential operations and registers.   3. Digital Signal Processors (DSPs) i.e. multipliers and adders.   4. Internal 9K-bit memory modules that may be used as, and not limited to be used as, Read Only Memory (ROM) LUTs, Random Access Memory (RAM) LUTs, and First In First Out memories (FIFOs). In embodiments, size of the memory modules may vary with other FPGA families. In an example, 18 bit data output may be generated in response to a 9 bit input address.   

     Embodiments of the present specification are implemented as firmware, i.e. a logic module instantiated in FPGA  402 . The implementation may operate simultaneously on live video from multiple viewing elements, where each video may be processed independently. The embodiments may be implemented in the video processing pipeline between the de-mosaic stage (sensors&#39; DSPs outputs) and the frame grabber input (one of four, used for rescaling, zoom, etc.). The implementation in accordance with various embodiments may be optionally bypassed by activating an FPGA-internal logic switch  480  or by setting clipping thresholds to zero, or by setting interpolator to bypass the CDFs. Following are some of the advantages of using an FPGA implementation in embodiments of the present specification:
     1. Reliability. FPGA is a firmware (i.e. hardware) application resulting in reliability in one or more of the following forms:
       Algorithm can run even when the software crashes. This is beneficial during real-time procedures in clinics.   Hardware/firmware is less likely to crash in real-time, than software.   Once simulated and tested thoroughly, unexpected failures are less likely to occur, compared with software.   The algorithm, as well as all other image processing modules, can start running quickly after system power-up, without having to wait for the much slower software booting. In an embodiment, they can start running within three seconds.   
       2. Availability. The use of a General Processing Unit (GPU) may be avoided in the system. The GPU may compliment the FPGA but may not replace it. Limitations to using a GPU may include:
       An extra module that can crash in real-time operation, especially when it relies on software for its operation.   Higher BOM cost.   Longer system assembly phase.   More complex system maintenance.   Additional software engineers to program and debug the GPU.   Bigger system size.   Higher power consumption (approximately 150 W or more, compared with FPGA&#39;s approximately 8.5 W in embodiments of the specification). Higher power consumption could imply an extra size and cost of system power supply and higher heat dissipation, requiring a stronger fan resulting in a higher acoustic noise.   
       3. Complementing the GPU. Even if the system does include a GPU, it is still worthwhile to relieve it from the task of running the algorithm (therefore assigning the task to the FPGA) as the algorithm introduces a heavy computational load on the GPU to the point where it could get in the GPU&#39;s way of running other important algorithms such as, for example, pattern recognition, 3D imaging, real-time OSD etc.   4. Architecture. Experience shows that a non-GPU based computer is overwhelmingly under powered for running the algorithm, as the maximal equivalent ingress frame rate it can handle drops dramatically to about ˜1-3 per second. In general, the internal architecture of an FPGA that allows performing thousands of tasks simultaneously, in parallel (even at the cost of a slower clock—about ˜ 1/20 of a processor) is more suitable for this type of application.   

       FIG. 5A  is a flowchart illustrating the steps of enhancing images obtained by a multiple viewing elements endoscope system using a contrast limited adaptive histogram equalization (CLAHE) algorithm, in accordance with an embodiment of the present specification. At step  502  one or more YCbCr color space video streams each obtained from one or more viewing elements of an endoscope are input to an adapter of an FPGA within the endoscope&#39;s main controller circuit. In some embodiments, YCbCr input from each of at least two viewing elements of the endoscope is input to the adapter. In some embodiments, each YCbCr input is 8 bit, 10 bit, or of any other length per component. In one embodiment, the YCbCr input is of 10 bit per component. 
     At step  504 , each of the one or more YCbCr color space video streams are converted to corresponding number of Lab color space video streams within said adapter. In some embodiments, each YCbCr input including 10 bit per color component is converted by the adapter to a 12 bit per component Lab color space video stream, of which all 12 bits are used for the L component, whereas 10 bits are used for each of a and b color components, totaling 32 bits per Lab pixel. 
     At step  506  each of the said one or more Lab color space video streams are pushed to a frame grabber on said FPGA and at step  508  said one or more Lab color space video streams are grabbed as corresponding one or more Lab color space frames within said frame grabber. In some embodiments, the frame grabber is fed by two Lab color space video streams, each coming from a distinct viewing element of the endoscope. 
     At step  510  said one or more Lab color space frames are fetched from the frame grabber using a fetching module on said FPGA. The fetching module may keep track of the ingress video frame timing (i.e. line count) and may instruct the frame grabber regarding which rows to fetch from an associated memory device. These rows are calculated from the video lines that may be needed to be displayed, and which are at constant phase shift relative to the ingress frame. At step  512 , Lab color space frame data of the one or more Lab color space frames within said fetching module is rearranged to generate one or more delayed Lab streams corresponding to the one or more Lab color space frames pulled by the fetching module. At step  514 , said one or more delayed Lab streams are pushed to one or more separate modules within an interpolation algorithm on said FPGA, each delayed Lab stream being fed to a distinct module within the interpolation algorithm. At step  516 , the one or more delayed Lab streams are processed with said CLAHE algorithm within said separate modules to generate corresponding one or more contrast enhanced Lab streams. In various embodiments, data from fetched rows is rearranged by the fetching module to a format understood by the interpolation algorithm. In an embodiment, the data from the fetched rows may include two video streams (one per each viewing element) where each video stream comprises Lab components. The delayed Lab streams, corresponding to each viewing element, are fed to separate modules within the interpolation algorithm where they are similarly processed in accordance with the CLAHE algorithm as described in the present specification. 
       FIG. 5B  is a flowchart illustrating the steps of enhancing images obtained by an endoscope system having three viewing elements, by using a contrast limited adaptive histogram equalization (CLAHE) algorithm, in accordance with an embodiment of the present specification. At step  520  three YCbCr color space video streams, each obtained from one of the three viewing elements of the endoscope, are input to an adapter of an FPGA within the endoscope&#39;s main controller circuit. In some embodiments, each YCbCr input is 8 bit, 10 bit, or of any other length per component. In one embodiment, the YCbCr input is of 10 bit per component. 
     At step  522 , each of the three YCbCr color space video streams are converted to three Lab color space video streams respectively within said adapter. In some embodiments, each YCbCr input including 10 bit per color component is converted by the adapter to a 12 bit per component Lab color space video stream, of which all 12 bits are used for the L component, whereas 10 bits are used for each of a and b color components, totaling 32 bits per Lab pixel. 
     At step  524  each of the three Lab color space video streams are pushed to a frame grabber on said FPGA and at step  526  the three Lab color space video streams are grabbed as corresponding three Lab color space frames within said frame grabber. In some embodiments, the frame grabber&#39;s Y input is fed by a left viewing element&#39;s Lab, Cb input by a central viewing element&#39;s Lab, and Cr input by a right viewing element&#39;s Lab—i.e., frame grabber is fed by three viewing elements. This mode of operation may be advantageous in using a single frame grabber (for use with one camera endoscopes in accordance with some embodiments) with a multiple camera endoscope. 
     At step  528  the three Lab color space frames are fetched from the frame grabber using a fetching module on said FPGA. The fetching module may keep track of the ingress video frame timing (i.e. line count) and may instruct the frame grabber regarding which rows to fetch from an associated memory device. These rows are calculated from the video lines that may be needed to be displayed, and which are at constant phase shift relative to the ingress frame. At step  530 , Lab color space frame data of the three Lab color space frames within said fetching module is rearranged to generate three delayed Lab streams, each corresponding to one of the three Lab color space frames pulled by the fetching module. At step  532 , the three delayed Lab streams are pushed to three separate modules within an interpolation algorithm on said FPGA, each delayed Lab stream being fed to a distinct module within the interpolation algorithm. At step  534 , the three delayed Lab streams are processed with said CLAHE algorithm within said separate modules to generate corresponding three contrast enhanced Lab streams. In various embodiments, data from fetched rows is rearranged by the fetching module to a format understood by the interpolation algorithm. In an embodiment, the data from the fetched rows may include three video streams (one per each viewing element) where each video stream comprises Lab components. The delayed Lab streams, corresponding to each viewing element, are fed to separate modules within the interpolation algorithm where they are similarly processed in accordance with the CLAHE algorithm as described in the present specification. At step  536 , each contrast enhanced Lab stream is displayed as a contrast enhanced image on one or more display devices coupled with the controller. 
       FIG. 6A  illustrates a process pipeline that converts YCbCr color space to Lab color space, in accordance with embodiments of the specification. This is done in the Lab,  10   b  ( 12   b , in some embodiments) modules  406  within the adapter  405  shown in  FIG. 4A . YCbCr components, or any other color space components, originating from the camera undergo these processes using linear and non-linear operators. In embodiments, the MADs multiply a three-component vector by a designated 3×3 matrix, then add another 3-component designated vector. The matrices and vectors may be unique for each MAD instantiation. Also, in embodiments, LUTs may operate independently and simultaneously on the three components of the input vector, to perform non-linear functions. The non-linear functions may be unique for each LUT instantiation. Within a LUT, the same function may be applied to all three components. 
     The conversion process of  FIG. 6A  is illustrated for one camera, and may be explained in five steps. At step  602 , a MAD instantiation performs YCbCr to RGB conversion. At  604 , a LUT performs a function similar to Y(x)=x{circumflex over ( )}2.40 (Inverse Gamma correction, known to those skilled in the art). At  606 , a MAD instantiation performs RGB to XYZ conversion. At  608 , a LUT executes a function similar to Y(x)=x{circumflex over ( )}0.33 necessary for the Lab conversion, which is known to those skilled in the art. At  610 , a MAD instantiation performs XYZ to Lab conversion excluding the non-linear function, performed already in previous step  608 . 
       FIG. 6B  is a flowchart illustrating the steps performed by the process pipeline shown in  FIG. 6A . At step  6102  a YCbCr color space video stream is input to a MAD instantiation for conversion to a RGB format. At step  6104  an inverse Gama correction is applied to the output RGB data by using a LUT. In an embodiment, a function similar to Y(x)=x{circumflex over ( )}2.40 is applied to the RGB data. At step  6106 , the corrected RGB data output at step  6104  is input to a MAD instantiation for conversion to a XYZ format. At step  6108  a correction function is applied to the output XYZ data by using a LUT. In an embodiment, a function similar to Y(x)=x{circumflex over ( )}0.33 is applied to the XYZ data. At step  6120 , the corrected XYZ data output at step  6108  is input to a MAD instantiation and converted to a LAB format. 
       FIG. 7A  illustrates a process pipeline that converts Lab color space to YCbCr (or any other) color space, in accordance with embodiments of the specification. This is done in modules  430  shown in  FIG. 4A . The pipeline shown in  FIG. 7A  is the inverse of the pipeline shown in  FIG. 6A . A Lab format may not enable screens to display video images effectively, therefore they are converted back to YCbCr (or any other color space) that may be compatible with one or more displays used with the endoscope system. 
     The conversion process of  FIG. 7A  is illustrated for one camera, and may be explained in a plurality of steps, and in one embodiment, five steps. At step  702  a MAD instantiation performs Lab to XYZ conversion excluding the non-linear function, performed in the next step and is known to those skilled in the art. At the next step  704 , a LUT executes a function similar to Y(x)=x{circumflex over ( )}3.00. At step  706 , a MAD instantiation performs XYZ to RGB conversion. At step  708 , a LUT executes a function similar to Y(x)=x{circumflex over ( )}(1/2.40) (Gamma correction). At step  710 , a MAD instantiation performs RGB to YCbCr conversion. In some embodiments, modules  430  of  FIG. 4A  may include a decimator for converting the YCbCr 4:4:4 at the output of step  520 , to YCbCr 4:2:2. 
       FIG. 7B  is a flowchart illustrating the steps performed by the process pipeline shown in  FIG. 7A . At step  7102  a LAB color space video stream is input to a MAD instantiation for conversion to a XYZ format. At step  7104  a correction function is applied to the output XYZ data by using a LUT. In an embodiment, a function similar to Y(x)=x{circumflex over ( )}3.00 is applied to the XYZ data. At step  7106 , the corrected XYZ data output at step  7104  is input to a MAD instantiation for conversion to a RGB format. At step  7108  an inverse Gama correction function is applied to the output RGB data by using a LUT. In an embodiment, a function similar to Y(x)=x{circumflex over ( )}(1/2.40) is applied to the RGB data. At step  7120 , the corrected RGB data, output at step  7108  is input to a MAD instantiation and converted to a to YCbCr format. 
       FIG. 8A  illustrates a traditional image  802  captured by an endoscope placed inside a body cavity.  FIG. 8B  illustrates the image of  FIG. 8A  enhanced by using the method of the present specification. Image  804  presents a highly enhanced image as compared to image  802  resulting from user&#39;s control over contrast and noise in accordance with the embodiments of the present specification. 
     Advantages of FPGA firmware implementation for image enhancement were discussed above. Embodiments of the present specification allow image enhancement during real time video capture and display, in addition to enabling image enhancement of still images. Moreover, embodiments of the specification operate on Lab color space, thus allowing greater contrast enhancement abilities. Additionally, tile overlapping, as described in embodiments above further enhance traditional CLAHE implementations. Yet another step for enhancement is the use of bi-cubic interpolation for inter-tile interpolation. The various advantages are applicable simultaneously to videos captured by multiple viewing elements in an endoscope system. 
     The above examples are merely illustrative of the many applications of the system of present invention. Although only a few embodiments of the present invention have been described herein, it should be understood that the present invention might be embodied in many other specific forms without departing from the spirit or scope of the invention. Therefore, the present examples and embodiments are to be considered as illustrative and not restrictive, and the invention may be modified within the scope of the appended claims.