Patent Publication Number: US-11398011-B2

Title: Super resolution and color motion artifact correction in a pulsed laser mapping imaging system

Description:
CROSS-REFERENCE TO RELATED APPLICATIONS 
     This application claims the benefit of U.S. Provisional Patent Application No. 62/864,213, filed Jun. 20, 2019, titled “SUPER RESOLUTION AND COLOR MOTION ARTIFACT CORRECTION IN A PULSED HYPERSPECTRAL AND FLUORESCENCE IMAGING SYSTEM,” which is incorporated herein by reference in its entirety, including but not limited to those portions that specifically appear hereinafter, the incorporation by reference being made with the following exception: In the event that any portion of the above-referenced provisional application is inconsistent with this application, this application supersedes the above-referenced provisional application. 
    
    
     TECHNICAL FIELD 
     This disclosure is directed to digital imaging and is particularly directed to laser mapping imaging in a light deficient environment. 
     BACKGROUND 
     Advances in technology have provided advances in imaging capabilities for medical use. An endoscope may be used to look inside a body and examine the interior of an organ or cavity of the body. Endoscopes are used for investigating a patient&#39;s symptoms, confirming a diagnosis, or providing medical treatment. A medical endoscope may be used for viewing a variety of body systems and parts such as the gastrointestinal tract, the respiratory tract, the urinary tract, the abdominal cavity, and so forth. Endoscopes may further be used for surgical procedures such as plastic surgery procedures, procedures performed on joints or bones, procedures performed on the neurological system, procedures performed within the abdominal cavity, and so forth. 
     In some instances of endoscopic imaging, it may be beneficial or necessary to view a space in color. A digital color image includes at least three layers, or “color channels,” that cumulatively form an image with a range of hues. Each of the color channels measures the intensity and chrominance of light for a spectral band. Commonly, a digital color image includes a color channel for red, green, and blue spectral bands of light (this may be referred to as a Red Green Blue or RGB image). Each of the red, green, and blue color channels include brightness information for the red, green, or blue spectral band of light. The brightness information for the separate red, green, and blue layers are combined to create the color image. Because a color image is made up of separate layers, a conventional digital camera image sensor includes a color filter array that permits red, green, and blue visible light wavelengths to hit selected pixel sensors. Each individual pixel sensor element is made sensitive to red, green, or blue wavelengths and will only return image data for that wavelength. The image data from the total array of pixel sensors is combined to generate the RGB image. The at least three distinct types of pixel sensors consume significant physical space such that the complete pixel array cannot fit in the small distal end of an endoscope. 
     Because a traditional image sensor cannot fit in the distal end of an endoscope, the image sensor is traditionally located in a handpiece unit of an endoscope that is held by an endoscope operator and is not placed within the body cavity. In such an endoscope, light is transmitted along the length of the endoscope from the handpiece unit to the distal end of the endoscope. This configuration has significant limitations. Endoscopes with this configuration are delicate and can be easily misaligned or damaged when bumped or impacted during regular use. This can significantly degrade the quality of the images and necessitate that the endoscope be frequently repaired or replaced. 
     The traditional endoscope with the image sensor placed in the handpiece unit is further limited to capturing only color images. However, in some implementations, it may be desirable to capture images with laser mapping image data in addition to color image data. Laser mapping imaging can capture the surface shape of objects and landscapes and measure distances between objects within a scene. In some implementations, it may be desirable to measure distances and surface shapes within a body cavity during an endoscopic imaging procedure. 
     However, applications of laser mapping technology known in the art typically require highly specialized equipment that may not be useful for multiple applications. Further, laser mapping technology provides a limited view of an environment and typically must be used in conjunction with multiple separate systems. In the context of endoscopic medical imaging procedures, all sensors must fit within a small physical area within a body cavity. In some instances, the geographic area is exceptionally small and may only accommodate a very small tip of an endoscope. As such, medical endoscopes known in the art are necessarily small and cannot accommodate multiple distinct imaging and ranging systems. It is therefore desirable to develop an endoscopic imaging system that is capable of generating laser mapping data in a small space such as a body cavity. 
     In light of the foregoing, described herein are systems, methods, and devices for laser mapping imaging in a light deficient environment. Such systems, methods, and devices may provide multiple datasets for identifying critical structures in a body and providing precise and valuable information about a body cavity. 
    
    
     
       BRIEF DESCRIPTION OF THE DRAWINGS 
       Non-limiting and non-exhaustive implementations of the disclosure are described with reference to the following figures, wherein like reference numerals refer to like parts throughout the various views unless otherwise specified. Advantages of the disclosure will become better understood with regard to the following description and accompanying drawings where: 
         FIG. 1  is a schematic view of a system for digital imaging in a light deficient environment with a paired emitter and pixel array; 
         FIG. 2  is a system for providing illumination to a light deficient environment for endoscopic imaging; 
         FIG. 2A  is a schematic diagram of complementary system hardware; 
         FIGS. 3A to 3D  are illustrations of the operational cycles of an image sensor used to construct one or more exposure frames; 
         FIG. 4A  is a graphical representation of the operation of an embodiment of an electromagnetic emitter; 
         FIG. 4B  is a graphical representation of varying the duration and magnitude of the emitted electromagnetic pulse to provide exposure control; 
         FIG. 5  is a graphical representation of an embodiment of the disclosure combining the operational cycles of an image sensor, an electromagnetic emitter, and the emitted electromagnetic pulses of  FIGS. 3A-4A , which demonstrate the imaging system during operation; 
         FIG. 6A  is a schematic diagram of a process for recording a video with full spectrum light over a period of time from t( 0 ) to t( 1 ); 
         FIG. 6B  is a schematic diagram of a process for recording a video by pulsing portioned spectrum light over a period of time from t( 0 ) to t( 1 ); 
         FIGS. 7A-7E  illustrate schematic views of processes over an interval of time for recording a frame of video for both full spectrum light and partitioned spectrum light; 
         FIG. 8  is a schematic diagram of a process flow to be implemented by a controller or image signal processor for generating a video stream with RGB image frames and laser mapping data overlaid on the RGB image frame; 
         FIG. 9  is a schematic diagram of a process flow for applying super resolution and color motion artifact correction processes to image data that may include luminance, chrominance, and laser mapping data for generating a YCbCr or RGB image with laser mapping data overlaid thereon; 
         FIG. 10  is a schematic of an example pixel array configured in an x and y plane that may be used to implement the process flow illustrated in  FIG. 9  for applying the super resolution and color motion artifact correction processes to image data; 
         FIG. 11  is a schematic of an example pixel array wherein luminance pixels are shifted in the x and y directions for comparing pixel data to an equivalent block in that location in a different exposure frame in furtherance of applying super resolution and color motion artifact processes to image data; 
         FIG. 12  illustrates an example scene wherein a ball is traveling through the scene at a quicker rater than the rate of capture for multiple exposure frames sensed by a pixel array of an image sensor; 
         FIG. 13  is a schematic diagram of a pattern reconstruction process for generating an RGB image frame with laser mapping image data overlaid thereon; 
         FIGS. 14A-14C  illustrate a light source having a plurality of emitters; 
         FIG. 15  illustrates a single optical fiber outputting via a diffuser at an output to illuminate a scene in a light deficient environment; 
         FIG. 16  illustrates a portion of the electromagnetic spectrum divided into a plurality of different sub-spectrums which may be emitted by emitters of a light source in accordance with the principles and teachings of the disclosure; 
         FIG. 17  is a schematic diagram illustrating a timing sequence for emission and readout for generating an image frame comprising a plurality of exposure frames resulting from differing partitions of pulsed light; 
         FIG. 18  illustrates an imaging system including a single cut filter for filtering wavelengths of electromagnetic radiation; 
         FIG. 19  illustrates an imaging system comprising a multiple cut filter for filtering wavelengths of electromagnetic radiation; 
         FIG. 20  illustrates an example laser mapping pattern that may be pulsed by an imaging system; 
         FIGS. 21A and 21B  illustrate a perspective view and a side view, respectively, of an implementation of an imaging sensor built on a plurality of substrates, wherein a plurality of pixel columns forming the pixel array are located on the first substrate and a plurality of circuit columns are located on a second substrate and showing an electrical connection and communication between one column of pixels to its associated or corresponding column of circuitry; 
         FIGS. 22A and 22B  illustrate a perspective view and a side view, respectively, of an implementation of an imaging sensor having a plurality of pixel arrays for producing a three-dimensional image, wherein the plurality of pixel arrays and the image sensor are built on a plurality of substrates; and 
         FIGS. 23A and 23B  illustrate an implementation having a plurality of pixel arrays for producing a three-dimensional image in accordance with the principles and teachings of the disclosure. 
     
    
    
     DETAILED DESCRIPTION 
     Disclosed herein are systems, methods, and devices for digital imaging that may be primarily suited to medical applications such as medical endoscopic imaging. An embodiment of the disclosure is an endoscopic system for laser mapping and/or color imaging in a light deficient environment. 
     Conventional endoscopes are designed such that the image sensor is placed at a proximal end of the device within a handpiece unit. This configuration requires that incident light travel the length of the endoscope by way of precisely coupled optical elements. The precise optical elements can easily be misaligned during regular use, and this can lead to image distortion or image loss. Embodiments of the disclosure place an image sensor within a distal end of the endoscope itself. This provides greater optical simplicity when compared with implementations known in the art. However, an acceptable solution to this approach is by no means trivial and introduces its own set of engineering challenges, not least of which that the image sensor must fit within a highly constrained area. 
     The imaging systems disclosed herein place aggressive constraints on the size of the image sensor. This enables the image sensor to be placed in a distal end of an endoscope and thereby enables the corresponding benefits of improved optical simplicity and increased mechanical robustness for the endoscope. However, placing these aggressive constraints on the image sensor area results in fewer and/or smaller pixels and can degrade image quality. An embodiment of the disclosure overcomes this challenge by incorporating a monochrome image sensor with minimal peripheral circuitry, connection pads, and logic. The imaging systems disclosed herein provide means for extending the dynamic range, sensor sensitivity, and spatial resolution of resultant images while still decreasing the overall size of the image sensor through the application of super resolution and color motion artifact correction algorithms. 
     In an embodiment, the super resolution algorithm is deployed to enhance perceived resolution of an image and extract motion information from a series of sequential exposure frames that are captured sequentially in time. Each of the sequential exposure frames is generated by a pixel array of an image sensor. The pixel array senses reflected electromagnetic radiation from a pulse of electromagnetic radiation that is emitted by an emitter. The pulses of electromagnetic radiation may include red, green, blue, and/or laser mapping pulses for generating red exposure frames, green exposure frames, blue exposure frames, and/or laser mapping exposure frames. A grouping of sequential exposure frames are combined to generate an image frame with increased spatial resolution when compared with the individual exposure frames. The super resolution algorithm and the color motion artifact correction processes disclosed herein detect motion in a scene, correct for the detected motion, and increase spatial resolution of a resultant image frame by combining multiple exposure frames. 
     For digital imaging systems, the final quality of a video stream depends on engineering details of the electronic capture process deployed by the image sensor. The perceived quality of an image frame is dependent on, among other things, the signal to noise ratio (SNR), the dynamic range (DR), the spatial resolution, the perception of visible unnatural artifacts, the perception of spatial distortion, and the color fidelity and appeal of the image frame. Each of these factors can be negatively impacted by decreasing the overall size of the image sensor. Therefore, in an effort to increase the perceived quality of a resultant image frame, traditional cameras known in the art include multiple image sensors or include an enlarged image sensor. For example, high-end cameras that can produce high resolution images typically include at least three monochrome sensors that are precisely coupled in an elaborate arrangement of prisms and filters. Another traditional solution is to use a single sensor with individual pixel-sized color filters fabricated on to the image sensor in a mosaic arrangement. The most popular mosaic arrangement is the Bayer pattern. An image sensor with a Bayer pattern can be inexpensive to fabricate but cannot achieve the image quality realized by the three-image sensor solution implemented in high-end cameras. An additional undesirable side effect of the Bayer pattern is that the color segmentation pattern introduces artifacts in the resultant image frames, and these artifacts can be especially noticeable around black and white edges. 
     One traditional approach to decreasing the size of the image sensor is to increase the number of pixels in the pixel array and reduce the size of the individual pixels. However, smaller pixels naturally have lower signal capacity. The lower signal capacity reduces the dynamic range of data captured by the pixels and reduces the maximum possible signal to noise ratio. Decreasing the area of an individual pixel reduces the sensitivity of the pixel not only in proportion with the capture area of the pixel but to a greater degree. The loss of sensitivity for the pixel may be compensated by widening the aperture, but this leads to a shallower depth of field and shallower depth of focus. The shallower depth of field impacts the resolution of the resultant image and can lead to greater spatial distortion. Additionally, smaller pixels are more challenging to manufacture consistently, and this may result in greater defect rates. 
     In light of the deficiencies associated with decreasing the capture area of the pixels, disclosed herein are systems, methods, and devices for reducing pixel count and bolstering image resolution by other means. In an embodiment, a monochrome image sensor is used with “color agnostic” pixels in the pixel array. The color information is determined by capturing independent exposure frames in response to pulses of different wavelengths of electromagnetic radiation. The alternative pulses may include red, green, and blue wavelengths for generating an RGB image frame consisting of a red exposure frame, a green exposure frame, and a blue exposure frame. The image frame may further include data from a laser mapping exposure frame overlaid on the RGB image frame. The laser mapping pulse may include one or more pulses of electromagnetic radiation for measuring distances, dimensions, and three-dimensional topologies within a scene. 
     In an embodiment, each pulse or grouping of pulses of electromagnetic radiation results in an exposure frame sensed by the pixel array. A plurality of exposure frames may be combined to generate an image frame. The image frame may include, for example, a red exposure frame generated in response to a red pulse, a green exposure frame generated in response to a green pulse, a blue exposure frame generated in response to a blue pulse, and a laser mapping exposure frame generated in response to a laser mapping pulse. The red, green, blue, and laser mapping exposure frames can be combined to generate a single RGB image frame with laser mapping data overlaid thereon. This method results in increased dynamic range and spatial resolution in the resultant image frame. However, this method can introduce motion blur because the multiple exposure frames making up the image frame are captured over time. Additionally, because the independent exposure frames supply different color components, the image frame can have unnatural colored effects that may be particularly visible in the vicinity of large edges. In light of the foregoing, the systems, methods, and devices disclosed herein correct for motion introduced by frame-wise color switching. 
     In some instances, it is desirable to generate endoscopic imaging with multiple data types or multiple images overlaid on one another. For example, it may be desirable to generate an RGB image frame that further includes laser mapping imaging data overlaid on the RGB image frame. An overlaid image of this nature may enable a medical practitioner or computer program to identify distances, dimensions, and topologies of critical body structures based on the laser mapping imaging data. Historically, this would require the use of multiple sensor systems including an image sensor for color imaging and one or more additional image sensors for laser mapping imaging. In such systems, the multiple image sensors would have multiple types of pixel sensors that are each sensitive to distinct ranges of electromagnetic radiation. In systems known in the art, this includes the three separate types of pixel sensors for generating an RGB color image along with additional pixel sensors for generating the laser mapping image data at different wavelengths of the electromagnetic spectrum. Traditionally, these multiple different pixel arrays consume a prohibitively large physical space and cannot be located at a distal tip of the endoscope. Considering the foregoing, disclosed herein are systems, methods, and devices for endoscopic imaging in a light deficient environment. The systems, methods, and devices disclosed herein provide means for employing multiple imaging techniques in a single imaging session while permitting one or more image sensors to be disposed in a distal tip of the endoscope. 
     Laser Mapping Imaging 
     In an embodiment, the systems, methods, and devices disclosed herein provide means for generating laser mapping data with an endoscopic imaging system. Laser mapping data can be used to determine precise measurements and topographical outlines of a scene. In one implementation, laser mapping data is used to determine precise measurements between, for example, structures or organs in a body cavity, devices or tools in the body cavity, and/or critical structures in the body cavity. As discussed herein, the term “laser mapping” may encompass technologies referred to as laser mapping, laser scanning, topographical scanning, three-dimensional scanning, laser tracking, tool tracking, and others. A laser mapping exposure frame as discussed herein may include topographical data for a scene, dimensions between objects or structures within a scene, dimensions or distances for tools or objects within a scene, and so forth. 
     Laser mapping generally includes the controlled deflection of laser beams. Within the field of three-dimensional object scanning, laser mapping combines controlled steering of laser beams with a laser rangefinder. By taking a distance measurement at every direction, the laser rangefinder can rapidly capture the surface shape of objects, tools, and landscapes. Construction of a full three-dimensional topology may include combining multiple surface models that are obtained from different viewing angles. Various measurement systems and methods exist in the art for applications in archaeology, geography, atmospheric physics, autonomous vehicles, and others. One such system includes light detection and ranging (LIDAR), which is a three-dimensional laser mapping system. LIDAR has been applied in navigation systems such as airplanes or satellites to determine position and orientation of a sensor in combination with other systems and sensors. LIDAR uses active sensors to illuminate an object and detect energy that is reflected off the object and back to a sensor. 
     As discussed herein, the term “laser mapping” includes laser tracking. Laser tracking, or the use of lasers for tool tracking, measures objects by determining the positions of optical targets held against those objects. Laser trackers can be accurate to the order of 0.025 mm over a distance of several meters. In an embodiment, an endoscopic imaging system pulses light for use in conjunction with a laser tracking system such that the position or tools within a scene can be tracked and measured. In such an embodiment, the endoscopic imaging system may pulse a laser tracking pattern on a tool, object, or other structure within a scene being imaged by the endoscopic imaging system. A target may be placed on the tool, object, or other structure within the scene. Measurements between the endoscopic imaging system and the target can be triggered and taken at selected points such that the position of the target (and the tool, object, or other structure to which the target is affixed) can be tracked by the endoscopic imaging system. 
     Pulsed Imaging 
     Some implementations of the disclosure include aspects of a combined sensor and system design that allows for high definition imaging with reduced pixel counts in a controlled illumination environment. This is accomplished with frame-by-frame pulsing of a single-color wavelength and switching or alternating each frame between a single, different color wavelength using a controlled light source in conjunction with high frame capture rates and a specially designed corresponding monochromatic sensor. The pixels may be color agnostic such that each pixel generates data for each pulse of electromagnetic radiation, including pulses for red, green, and blue visible light wavelengths along with other wavelengths used for laser mapping imaging. 
     For the purposes of promoting an understanding of the principles in accordance with the disclosure, reference will now be made to the embodiments illustrated in the drawings and specific language will be used to describe the same. It will nevertheless be understood that no limitation of the scope of the disclosure is thereby intended. Any alterations and further modifications of the inventive features illustrated herein, and any additional applications of the principles of the disclosure as illustrated herein, which would normally occur to one skilled in the relevant art and having possession of this disclosure, are to be considered within the scope of the disclosure claimed. 
     Before the structure, systems and methods for producing an image in a light deficient environment are disclosed and described, it is to be understood that this disclosure is not limited to the particular structures, configurations, process steps, and materials disclosed herein as such structures, configurations, process steps, and materials may vary somewhat. It is also to be understood that the terminology employed herein is used for the purpose of describing particular embodiments only and is not intended to be limiting since the scope of the disclosure will be limited only by the appended claims and equivalents thereof. 
     In describing and claiming the subject matter of the disclosure, the following terminology will be used in accordance with the definitions set out below. 
     It must be noted that, as used in this specification and the appended claims, the singular forms “a,” “an,” and “the” include plural referents unless the context clearly dictates otherwise. 
     As used herein, the terms “comprising,” “including,” “containing,” “characterized by,” and grammatical equivalents thereof are inclusive or open-ended terms that do not exclude additional, unrecited elements or method steps. 
     As used herein, the phrase “consisting of” and grammatical equivalents thereof exclude any element or step not specified in the claim. 
     As used herein, the phrase “consisting essentially of” and grammatical equivalents thereof limit the scope of a claim to the specified materials or steps and those that do not materially affect the basic and novel characteristic or characteristics of the claimed disclosure. 
     As used herein, the term “proximal” shall refer broadly to the concept of a portion nearest an origin. 
     As used herein, the term “distal” shall generally refer to the opposite of proximal, and thus to the concept of a portion farther from an origin, or a furthest portion, depending upon the context. 
     As used herein, color sensors or multi spectrum sensors are those sensors known to have a color filter array (CFA) thereon to filter the incoming electromagnetic radiation into its separate components. In the visual range of the electromagnetic spectrum, such a CFA may be built on a Bayer pattern or modification thereon to separate green, red and blue spectrum components of the light. 
     As used herein, monochromatic sensor refers to an unfiltered imaging sensor. Because the pixels are color agnostic, the effective spatial resolution is appreciably higher than for color (typically Bayer-pattern filtered) counterparts in conventional single-sensor cameras. Monochromatic sensors may also have higher quantum efficiency because fewer incident photons are wasted between individual pixels. 
     As used herein, an emitter is a device that is capable of generating and emitting electromagnetic pulses. Various embodiments of emitters may be configured to emit pulses and have very specific frequencies or ranges of frequencies from within the entire electromagnetic spectrum. Pulses may comprise wavelengths from the visible and non-visible ranges. An emitter may be cycled on and off to produce a pulse or may produce a pulse with a shutter mechanism. An emitter may have variable power output levels or may be controlled with a secondary device such as an aperture or filter. An emitter may emit broad spectrum or full spectrum electromagnetic radiation that may produce pulses through color filtering or shuttering. An emitter may comprise a plurality of electromagnetic sources that act individually or in concert. 
     It should be noted that as used herein the term “light” is both a particle and a wavelength and is intended to denote electromagnetic radiation that is detectable by a pixel array and may include wavelengths from the visible and non-visible spectrums of electromagnetic radiation. The term “partition” is used herein to mean a pre-determined range of wavelengths of the electromagnetic spectrum that is less than the entire spectrum, or in other words, wavelengths that make up some portion of the electromagnetic spectrum. As used herein, an emitter is a light source that may be controllable as to the portion of the electromagnetic spectrum that is emitted or that may operate as to the physics of its components, the intensity of the emissions, or the duration of the emission, or all the above. An emitter may emit light in any dithered, diffused, or collimated emission and may be controlled digitally or through analog methods or systems. As used herein, an electromagnetic emitter is a source of a burst of electromagnetic energy and includes light sources, such as lasers, LEDs, incandescent light, or any light source that can be digitally controlled. 
     Referring now to the figures,  FIG. 1  illustrates a schematic diagram of a system  100  for sequential pulsed imaging in a light deficient environment. The system  100  can be deployed to generate an RGB image with laser mapping data overlaid on the RGB image. The system  100  includes an emitter  102  and a pixel array  122 . The emitter  102  pulses a partition of electromagnetic radiation in the light deficient environment  112  and the pixel array  122  senses instances of reflected electromagnetic radiation. The emitter  102  and the pixel array  122  work in sequence such that one or more pulses of a partition of electromagnetic radiation results in image data sensed by the pixel array  122 . 
     It should be noted that as used herein the term “light” is both a particle and a wavelength and is intended to denote electromagnetic radiation that is detectable by a pixel array  122  and may include wavelengths from the visible and non-visible spectrums of electromagnetic radiation. The term “partition” is used herein to mean a pre-determined range of wavelengths of the electromagnetic spectrum that is less than the entire spectrum, or in other words, wavelengths that make up some portion of the electromagnetic spectrum. As used herein, an emitter is a light source that may be controllable as to the portion of the electromagnetic spectrum that is emitted or that may operate as to the physics of its components, the intensity of the emissions, or the duration of the emission, or all the above. An emitter may emit light in any dithered, diffused, or collimated emission and may be controlled digitally or through analog methods or systems. As used herein, an electromagnetic emitter is a source of a burst of electromagnetic energy and includes light sources, such as lasers, LEDs, incandescent light, or any light source that can be digitally controlled. 
     A pixel array  122  of an image sensor may be paired with the emitter  102  electronically, such that the emitter  102  and the pixel array  122  are synced during operation for both receiving the emissions and for the adjustments made within the system. The emitter  102  may be tuned to emit electromagnetic radiation in the form of a laser, which may be pulsed to illuminate a light deficient environment  112 . The emitter  102  may pulse at an interval that corresponds to the operation and functionality of the pixel array  122 . The emitter  102  may pulse light in a plurality of electromagnetic partitions such that the pixel array receives electromagnetic energy and produces a dataset that corresponds in time with each specific electromagnetic partition. For example,  FIG. 1  illustrates an implementation wherein the emitter  102  emits four different partitions of electromagnetic radiation, including red  104 , green  106 , blue  108  wavelengths, and a laser mapping  110  pulsing scheme. The laser mapping  110  pulsing scheme may include a grid pattern for identifying a topology  120  of a scene in the light deficient environment  112  and further for measuring dimensions and distances within the scene. The laser mapping  110  pulsing scheme is any suitable pulsing scheme or pattern that may be used for generating laser mapping image data. The laser mapping imaging data includes data generated by technologies known as laser mapping, laser scanning, topographical scanning, three-dimensional scanning, laser tracking, tool tracking, and others. 
     The light deficient environment  112  includes structures, tissues, and other elements that reflect a combination of red  114 , green  116 , and/or blue  118  light. A structure that is perceived as being red  114  will reflect back pulsed red  104  light. The reflection off the red structure results in sensed red  105  by the pixel array  122  following the pulsed red  104  emission. The data sensed by the pixel array  122  results in a red exposure frame. A structure that is perceived as being green  116  will reflect back pulsed green  106  light. The reflection off the green structure results in sensed green  107  by the pixel array  122  following the pulsed green  106  emission. The data sensed by the pixel array  122  results in a green exposure frame. A structure that is perceived as being blue  118  will reflect back pulsed blue  108  light. The reflection off the blue structure results in sensed blue  109  by the pixel array  122  following the pulsed blue  108  emission. The data sensed by the pixel array  122  results in a blue exposure frame. 
     When a structure is a combination of colors, the structure will reflect back a combination of the pulsed red  104 , pulsed green  106 , and/or pulsed blue  108  emissions. For example, a structure that is perceived as being purple will reflect back light from the pulsed red  104  and pulsed blue  108  emissions. The resulting data sensed by the pixel array  122  will indicate that light was reflected in the same region following the pulsed red  104  and pulsed blue  108  emissions. When the resultant red exposure frame and blue exposure frames are combined to form the RGB image frame, the RGB image frame will indicate that the structure is purple. 
     In an embodiment where the light deficient environment  112  includes a fluorescent reagent or dye or includes one or more fluorescent structures, tissues, or other elements, the pulsing scheme may include the emission of a certain fluorescence excitation wavelength. The certain fluorescence excitation wavelength may be selected to fluoresce a known fluorescent reagent, dye, or other structure. The fluorescent structure will be sensitive to the fluorescence excitation wavelength and will emit a fluorescence relaxation wavelength. The fluorescence relaxation wavelength will be sensed by the pixel array  122  following the emission of the fluorescence excitation wavelength. The data sensed by the pixel array  122  results in a fluorescence exposure frame. The fluorescence exposure frame may be combined with multiple other exposure frames to form an image frame. The data in the fluorescence exposure frame may be overlaid on an RGB image frame that includes data from a red exposure frame, a green exposure frame, and a blue exposure frame. 
     In an embodiment where the light deficient environment  112  includes structures, tissues, or other materials that emit a spectral response to certain partitions of the electromagnetic spectrum, the pulsing scheme may further include the emission of a hyperspectral partition of electromagnetic radiation for the purpose of eliciting the spectral response from the structures, tissues, or other materials present in the light deficient environment  112 . The spectral response includes the emission or reflection of certain wavelengths of electromagnetic radiation. The spectral response can be sensed by the pixel array  122  and result in a hyperspectral exposure frame. The hyperspectral exposure frame may be combined with multiple other exposure frames to form an image frame. The data in the hyperspectral exposure frame may be overlaid on an RGB image frame that includes data from a red exposure frame, a green exposure frame, and a blue exposure frame. 
     In an embodiment, the pulsing scheme includes the emission of a laser mapping  110  pattern. The reflected electromagnetic radiation sensed by the pixel array  122  following the emission of the laser mapping  110  pattern results in a laser mapping exposure frame that includes the sensed laser mapping  111  data. The data in the laser mapping exposure frame may be provided to a corresponding system to identify, for example, distances between tools present in the light deficient environment  112 , a three-dimensional surface topology of a scene in the light deficient environment  112 , distances, dimensions, or positions of structures or objects within the scene, distances dimensions, or positions of tools within the scene, and so forth. This data may be overlaid on an RGB image frame or otherwise provided to a user of the system. 
     The emitter  102  may be a laser emitter that is capable of emitting pulsed red  104  light for generating sensed red  105  data for identifying red  114  elements within the light deficient environment  112 . The emitter  102  is further capable of emitting pulsed green  106  light for generating sensed green  107  data for identifying green  116  elements within the light deficient environment. The emitter  102  is further capable of emitting pulsed blue  108  light for generating sensed blue  109  data for identifying blue  118  elements within the light deficient environment. The emitter  102  is further capable of emitting a laser mapping  110  pulsing scheme for mapping the topology  120  of a scene within the light deficient environment  112 . The emitter  102  is capable of emitting the pulsed red  104 , pulsed green  106 , pulsed blue  108 , and pulsed laser mapping  110  pulsing schemes in any desired sequence. 
     The pixel array  122  senses reflected electromagnetic radiation. Each of the sensed red  105 , the sensed green  107 , the sensed blue  109 , and the sensed laser mapping  111  data can be referred to as an “exposure frame.” Each exposure frame is assigned a specific color or wavelength partition, wherein the assignment is based on the timing of the pulsed color or wavelength partition from the emitter  102 . The exposure frame in combination with the assigned specific color or wavelength partition may be referred to as a dataset. Even though the pixels  122  are not color-dedicated, they can be assigned a color for any given dataset based on a priori information about the emitter. 
     For example, during operation, after pulsed red  104  light is pulsed in the light deficient environment  112 , the pixel array  122  senses reflected electromagnetic radiation. The reflected electromagnetic radiation results in an exposure frame, and the exposure frame is catalogued as sensed red  105  data because it corresponds in time with the pulsed red  104  light. The exposure frame in combination with an indication that it corresponds in time with the pulsed red  104  light is the “dataset.” This is repeated for each partition of electromagnetic radiation emitted by the emitter  102 . The data created by the pixel array  122  includes the sensed red  105  exposure frame identifying red  114  components in the light deficient environment and corresponding in time with the pulsed red  104  light. The data further includes the sensed green  107  exposure frame identifying green  116  components in the light deficient environment and corresponding in time with the pulsed green  106  light. The data further includes the sensed blue  109  exposure frame identifying blue  118  components in the light deficient environment and corresponding in time with the pulsed blue  108  light. The data further includes the sensed laser mapping  111  exposure frame identifying the topology  120  and corresponding in time with the laser mapping  110  pulsing scheme. 
     In one embodiment, three datasets representing RED, GREEN and BLUE electromagnetic pulses are combined to form a single image frame. Thus, the information in a red exposure frame, a green exposure frame, and a blue exposure frame are combined to form a single RGB image frame. One or more additional datasets representing other wavelength partitions may be overlaid on the single RGB image frame. The one or more additional datasets may represent, for example, the laser mapping data, fluorescence imaging data, and/or hyperspectral imaging data. 
     It will be appreciated that the disclosure is not limited to any particular color combination or any particular electromagnetic partition, and that any color combination or any electromagnetic partition may be used in place of RED, GREEN and BLUE, such as Cyan, Magenta and Yellow; Ultraviolet; infrared; any combination of the foregoing, or any other color combination, including all visible and non-visible wavelengths, without departing from the scope of the disclosure. In the figure, the light deficient environment  112  to be imaged includes red  114 , green  116 , and blue  118  portions, and further includes a topology  120  that can be sensed and mapped into a three-dimensional rendering. As illustrated in the figure, the reflected light from the electromagnetic pulses only contains the data for the portion of the object having the specific color that corresponds to the pulsed color partition. Those separate color (or color interval) datasets can then be used to reconstruct the image by combining the datasets at  126 . The information in each of the multiple exposure frames (i.e., the multiple datasets) may be combined by a controller  124 , a control unit, a camera control unit, the image sensor, an image signal processing pipeline, or some other computing resource that is configurable to process the multiple exposure frames and combine the datasets at  126 . The datasets may be combined to generate the single image frame within the endoscope unit itself or offsite by some other processing resource. 
       FIG. 2  is a system  200  for providing illumination to a light deficient environment, such as for endoscopic imaging. The system  200  may be used in combination with any of the systems, methods, or devices disclosed herein. The system  200  includes an emitter  202 , a controller  204 , a jumper waveguide  206 , a waveguide connector  208 , a lumen waveguide  210 , a lumen  212 , and an image sensor  214  with accompanying optical components (such as a lens). The emitter  202  (may be generically referred to as a “light source”) generates light that travels through the jumper waveguide  206  and the lumen waveguide  210  to illuminate a scene at a distal end of the lumen  212 . The emitter  202  may be used to emit any wavelength of electromagnetic energy including visible wavelengths, infrared, ultraviolet, hyperspectral, fluorescence excitation, or other wavelengths. The lumen  212  may be inserted into a patient&#39;s body for imaging, such as during a procedure or examination. The light is output as illustrated by dashed lines  216 . A scene illuminated by the light may be captured using the image sensor  214  and displayed for a doctor or some other medical personnel. The controller  204  may provide control signals to the emitter  202  to control when illumination is provided to a scene. In one embodiment, the emitter  202  and controller  204  are located within a camera control unit (CCU) or external console to which an endoscope is connected. If the image sensor  214  includes a CMOS sensor, light may be periodically provided to the scene in a series of illumination pulses between readout periods of the image sensor  214  during what is known as a blanking period. Thus, the light may be pulsed in a controlled manner to avoid overlapping into readout periods of the image pixels in a pixel array of the image sensor  214 . 
     In one embodiment, the lumen waveguide  210  includes one or more optical fibers. The optical fibers may be made of a low-cost material, such as plastic to allow for disposal of the lumen waveguide  210  and/or other portions of an endoscope. In one embodiment, the lumen waveguide  210  is a single glass fiber having a diameter of 500 microns. The jumper waveguide  206  may be permanently attached to the emitter  202 . For example, a jumper waveguide  206  may receive light from an emitter within the emitter  202  and provide that light to the lumen waveguide  210  at the location of the connector  208 . In one embodiment, the jumper waveguide  106  includes one or more glass fibers. The jumper waveguide may include any other type of waveguide for guiding light to the lumen waveguide  210 . The connector  208  may selectively couple the jumper waveguide  206  to the lumen waveguide  210  and allow light within the jumper waveguide  206  to pass to the lumen waveguide  210 . In one embodiment, the lumen waveguide  210  is directly coupled to a light source without any intervening jumper waveguide  206 . 
     The image sensor  214  includes a pixel array. In an embodiment, the image sensor  214  includes two or more pixel arrays for generating a three-dimensional image. The image sensor  214  may constitute two more image sensors that each have an independent pixel array and can operate independent of one another. The pixel array of the image sensor  214  includes active pixels and optical black (“OB”) or optically blind pixels. The active pixels may be clear “color agnostic” pixels that are capable of sensing imaging data for any wavelength of electromagnetic radiation. The optical black pixels are read during a blanking period of the pixel array when the pixel array is “reset” or calibrated. In an embodiment, light is pulsed during the blanking period of the pixel array when the optical black pixels are being read. After the optical black pixels have been read, the active pixels are read during a readout period of the pixel array. The active pixels may be charged by the electromagnetic radiation that is pulsed during the blanking period such that the active pixels are ready to be read by the image sensor during the readout period of the pixel array. 
       FIG. 2A  is a schematic diagram of complementary system hardware such as a special purpose or general-purpose computer. Implementations within the scope of the present disclosure may also include physical and other non-transitory computer readable media for carrying or storing computer executable instructions and/or data structures. Such computer readable media can be any available media that can be accessed by a general purpose or special purpose computer system. Computer readable media that stores computer executable instructions are computer storage media (devices). Computer readable media that carry computer executable instructions are transmission media. Thus, by way of example, and not limitation, implementations of the disclosure can comprise at least two distinctly different kinds of computer readable media: computer storage media (devices) and transmission media. 
     Computer storage media (devices) includes RAM, ROM, EEPROM, CD-ROM, solid state drives (“SSDs”) (e.g., based on RAM), Flash memory, phase-change memory (“PCM”), other types of memory, other optical disk storage, magnetic disk storage or other magnetic storage devices, or any other medium which can be used to store desired program code means in the form of computer executable instructions or data structures and which can be accessed by a general purpose or special purpose computer. 
     A “network” is defined as one or more data links that enable the transport of electronic data between computer systems and/or modules and/or other electronic devices. In an implementation, a sensor and camera control unit may be networked to communicate with each other, and other components, connected over the network to which they are connected. When information is transferred or provided over a network or another communications connection (either hardwired, wireless, or a combination of hardwired or wireless) to a computer, the computer properly views the connection as a transmission medium. Transmissions media can include a network and/or data links, which can be used to carry desired program code means in the form of computer executable instructions or data structures and which can be accessed by a general purpose or special purpose computer. Combinations of the above should also be included within the scope of computer readable media. 
     Further, upon reaching various computer system components, program code means in the form of computer executable instructions or data structures that can be transferred automatically from transmission media to computer storage media (devices) (or vice versa). For example, computer executable instructions or data structures received over a network or data link can be buffered in RAM within a network interface module (e.g., a “NIC”), and then eventually transferred to computer system RAM and/or to less volatile computer storage media (devices) at a computer system. RAM can also include solid state drives (SSDs or PCIx based real time memory tiered storage, such as FusionIO). Thus, it should be understood that computer storage media (devices) can be included in computer system components that also (or even primarily) utilize transmission media. 
     Computer executable instructions comprise, for example, instructions and data which, when executed by one or more processors, cause a general-purpose computer, special purpose computer, or special purpose processing device to perform a certain function or group of functions. The computer executable instructions may be, for example, binaries, intermediate format instructions such as assembly language, or even source code. Although the subject matter has been described in language specific to structural features and/or methodological acts, it is to be understood that the subject matter defined in the appended claims is not necessarily limited to the described features or acts described above. Rather, the described features and acts are disclosed as example forms of implementing the claims. 
     Those skilled in the art will appreciate that the disclosure may be practiced in network computing environments with many types of computer system configurations, including, personal computers, desktop computers, laptop computers, message processors, control units, camera control units, hand-held devices, hand pieces, multi-processor systems, microprocessor-based or programmable consumer electronics, network PCs, minicomputers, mainframe computers, mobile telephones, PDAs, tablets, pagers, routers, switches, various storage devices, and the like. It should be noted that any of the above-mentioned computing devices may be provided by or located within a brick and mortar location. The disclosure may also be practiced in distributed system environments where local and remote computer systems, which are linked (either by hardwired data links, wireless data links, or by a combination of hardwired and wireless data links) through a network, both perform tasks. In a distributed system environment, program modules may be located in both local and remote memory storage devices. 
     Further, where appropriate, functions described herein can be performed in one or more of: hardware, software, firmware, digital components, or analog components. For example, one or more application specific integrated circuits (ASICs) or field programmable gate arrays (FPGAs) can be programmed to carry out one or more of the systems and procedures described herein. Certain terms are used throughout the following description and Claims to refer to particular system components. As one skilled in the art will appreciate, components may be referred to by different names. This document does not intend to distinguish between components that differ in name, but not function. 
       FIG. 2A  is a block diagram illustrating an example computing device  250 . Computing device  250  may be used to perform various procedures, such as those discussed herein. Computing device  250  can function as a server, a client, or any other computing entity. Computing device  250  can perform various monitoring functions as discussed herein, and can execute one or more application programs, such as the application programs described herein. Computing device  250  can be any of a wide variety of computing devices, such as a desktop computer, a notebook computer, a server computer, a handheld computer, camera control unit, tablet computer and the like. 
     Computing device  250  includes one or more processor(s)  252 , one or more memory device(s)  254 , one or more interface(s)  256 , one or more mass storage device(s)  258 , one or more Input/Output (I/O) device(s)  260 , and a display device  280  all of which are coupled to a bus  262 . Processor(s)  252  include one or more processors or controllers that execute instructions stored in memory device(s)  254  and/or mass storage device(s)  258 . Processor(s)  252  may also include various types of computer readable media, such as cache memory. 
     Memory device(s)  254  include various computer readable media, such as volatile memory (e.g., random access memory (RAM)  264 ) and/or nonvolatile memory (e.g., read-only memory (ROM)  266 ). Memory device(s)  254  may also include rewritable ROM, such as Flash memory. 
     Mass storage device(s)  258  include various computer readable media, such as magnetic tapes, magnetic disks, optical disks, solid-state memory (e.g., Flash memory), and so forth. As shown in  FIG. 2 , a particular mass storage device is a hard disk drive  274 . Various drives may also be included in mass storage device(s)  258  to enable reading from and/or writing to the various computer readable media. Mass storage device(s)  258  include removable media  276  and/or non-removable media. 
     I/O device(s)  260  include various devices that allow data and/or other information to be input to or retrieved from computing device  250 . Example I/O device(s)  260  include digital imaging devices, electromagnetic sensors and emitters, cursor control devices, keyboards, keypads, microphones, monitors or other display devices, speakers, printers, network interface cards, modems, lenses, CCDs or other image capture devices, and the like. 
     Display device  280  includes any type of device capable of displaying information to one or more users of computing device  250 . Examples of display device  280  include a monitor, display terminal, video projection device, and the like. 
     Interface(s)  256  include various interfaces that allow computing device  250  to interact with other systems, devices, or computing environments. Example interface(s)  256  may include any number of different network interfaces  270 , such as interfaces to local area networks (LANs), wide area networks (WANs), wireless networks, and the Internet. Other interface(s) include user interface  268  and peripheral device interface  272 . The interface(s)  256  may also include one or more user interface elements  268 . The interface(s)  256  may also include one or more peripheral interfaces such as interfaces for printers, pointing devices (mice, track pad, etc.), keyboards, and the like. 
     Bus  262  allows processor(s)  252 , memory device(s)  254 , interface(s)  256 , mass storage device(s)  258 , and I/O device(s)  260  to communicate with one another, as well as other devices or components coupled to bus  262 . Bus  262  represents one or more of several types of bus structures, such as a system bus, PCI bus, IEEE 1394 bus, USB bus, and so forth. 
     For purposes of illustration, programs and other executable program components are shown herein as discrete blocks, although it is understood that such programs and components may reside at various times in different storage components of computing device  250  and are executed by processor(s)  252 . Alternatively, the systems and procedures described herein can be implemented in hardware, or a combination of hardware, software, and/or firmware. For example, one or more application specific integrated circuits (ASICs) or field programmable gate arrays (FPGAs) can be programmed to carry out one or more of the systems and procedures described herein. 
       FIG. 3A  illustrates the operational cycles of a sensor used in rolling readout mode or during the sensor readout  300 . The frame readout may start at and may be represented by vertical line  310 . The read-out period is represented by the diagonal or slanted line  302 . The active pixels of the pixel array of the image sensor may be read out on a row by row basis, the top of the downwards slanted edge being the sensor top row  312  and the bottom of the downwards slanted edge being the sensor bottom row  314 . The time between the last row readout and the next readout cycle may be called the blanking period  316 . It should be noted that some of the sensor pixel rows might be covered with a light shield (e.g., a metal coating or any other substantially black layer of another material type). These covered pixel rows may be referred to as optical black rows  318  and  320 . Optical black rows  318  and  320  may be used as input for correction algorithms. As shown in  FIG. 3A , these optical black rows  318  and  320  may be located on the top of the pixel array or at the bottom of the pixel array or at the top and the bottom of the pixel array. 
       FIG. 3B  illustrates a process of controlling the amount of electromagnetic radiation, e.g., light, that is exposed to a pixel, thereby integrated or accumulated by the pixel. It will be appreciated that photons are elementary particles of electromagnetic radiation. Photons are integrated, absorbed, or accumulated by each pixel and converted into an electrical charge or current. An electronic shutter or rolling shutter (shown by dashed line  322 ) may be used to start the integration time by resetting the pixel. The light will then integrate until the next readout phase. The position of the electronic shutter  322  can be moved between two readout cycles  302  to control the pixel saturation for a given amount of light. It should be noted that this technique allows for a constant integration time between two different lines but introduces a delay when moving from top to bottom rows. 
       FIG. 3C  illustrates the case where the electronic shutter  322  has been removed. In this configuration, the integration of the incoming light may start during readout  302  and may end at the next readout cycle  302 , which also defines the start of the next integration. 
       FIG. 3D  shows a configuration without an electronic shutter  322 , but with a controlled and pulsed light  330  during the blanking period  316 . This ensures that all rows see the same light issued from the same light pulse  330 . In other words, each row will start its integration in a dark environment, which may be at the optical black back row  320  of read out frame (m) for a maximum light pulse width, and will then receive a light strobe and will end its integration in a dark environment, which may be at the optical black front row  318  of the next succeeding read out frame (m+1) for a maximum light pulse width. In the  FIG. 3D  example, the image generated from the light pulse will be solely available during frame (m+1) readout without any interference with frames (m) and (m+2). It should be noted that the condition to have a light pulse to be read out only in one frame and not interfere with neighboring frames is to have the given light pulse firing during the blanking period  316 . Because the optical black rows  318 ,  320  are insensitive to light, the optical black back rows  320  time of frame (m) and the optical black front rows  318  time of frame (m+1) can be added to the blanking period  316  to determine the maximum range of the firing time of the light pulse  330 . 
     As illustrated in the  FIG. 3A , a sensor may be cycled many times to receive data for each pulsed color or wavelength (e.g., Red, Green, Blue, or other wavelength on the electromagnetic spectrum). Each cycle may be timed. In an embodiment, the cycles may be timed to operate within an interval of 16.67 ms. In another embodiment, the cycles may be timed to operate within an interval of 8.3 ms. It will be appreciated that other timing intervals are contemplated by the disclosure and are intended to fall within the scope of this disclosure. 
       FIG. 4A  graphically illustrates the operation of an embodiment of an electromagnetic emitter. An emitter may be timed to correspond with the cycles of a sensor, such that electromagnetic radiation is emitted within the sensor operation cycle and/or during a portion of the sensor operation cycle.  FIG. 4A  illustrates Pulse  1  at  402 , Pulse  2  at  404 , and Pulse  3  at  406 . In an embodiment, the emitter may pulse during the readout period  302  of the sensor operation cycle. In an embodiment, the emitter may pulse during the blanking portion  316  of the sensor operation cycle. In an embodiment, the emitter may pulse for a duration that is during portions of two or more sensor operational cycles. In an embodiment, the emitter may begin a pulse during the blanking portion  316 , or during the optical black portion  320  of the readout period  302 , and end the pulse during the readout period  302 , or during the optical black portion  318  of the readout period  302  of the next succeeding cycle. It will be understood that any combination of the above is intended to fall within the scope of this disclosure as long as the pulse of the emitter and the cycle of the sensor correspond. 
       FIG. 4B  graphically represents varying the duration and magnitude of the emitted electromagnetic pulse (e.g., Pulse  1  at  412 , Pulse  2  at  414 , and Pulse  3  at  416 ) to control exposure. An emitter having a fixed output magnitude may be pulsed during any of the cycles noted above in relation to  FIGS. 3D and 4A  for an interval to provide the needed electromagnetic energy to the pixel array. An emitter having a fixed output magnitude may be pulsed at a longer interval of time, thereby providing more electromagnetic energy to the pixels or the emitter may be pulsed at a shorter interval of time, thereby providing less electromagnetic energy. Whether a longer or shorter interval time is needed depends upon the operational conditions. 
     In contrast to adjusting the interval of time the emitter pulses a fixed output magnitude, the magnitude of the emission itself may be increased to provide more electromagnetic energy to the pixels. Similarly, decreasing the magnitude of the pulse provides less electromagnetic energy to the pixels. It should be noted that an embodiment of the system may have the ability to adjust both magnitude and duration concurrently, if desired. Additionally, the sensor may be adjusted to increase its sensitivity and duration as desired for optimal image quality.  FIG. 4B  illustrates varying the magnitude and duration of the pulses. In the illustration, Pulse  1  at  412  has a higher magnitude or intensity than either Pulse  2  at  414  or Pulse  3  at  416 . Additionally, Pulse  1  at  412  has a shorter duration than Pulse  2  at  414  or Pulse  3  at  416 , such that the electromagnetic energy provided by the pulse is illustrated by the area under the pulse shown in the illustration. In the illustration, Pulse  2  at  414  has a relatively low magnitude or intensity and a longer duration when compared to either Pulse  1  at  412  or Pulse  3  at  416 . Finally, in the illustration, Pulse  3  at  416  has an intermediate magnitude or intensity and duration, when compared to Pulse  1  at  412  and Pulse  2  at  414 . 
       FIG. 5  is a graphical representation of an embodiment of the disclosure combining the operational cycles, the electromagnetic emitter, and the emitted electromagnetic pulses of  FIGS. 3A-3D and 4A  to demonstrate the imaging system during operation in accordance with the principles and teachings of the disclosure. As can be seen in the figure, the electromagnetic emitter pulses the emissions primarily during the blanking period  316  of the image sensor such that the pixels will be charged and ready to read during the readout period  302  of the image sensor cycle. The dashed lines in  FIG. 5  represent the pulses of electromagnetic radiation (from  FIG. 4A ). The pulses of electromagnetic radiation are primarily emitted during the blanking period  316  of the image sensor but may overlap with the readout period  302  of the image sensor. 
     An exposure frame includes the data read by the pixel array of the image sensor during a readout period  302 . The exposure frame may be combined with an indication of what type of pulse was emitted by the emitter prior to the readout period  302 . The combination of the exposure frame and the indication of the pulse type may be referred to as a dataset. Multiple exposure frames may be combined to generate a black-and-white or RGB color image. Additionally, hyperspectral, fluorescence, and/or laser mapping imaging data may be overlaid on a black-and-white or RGB image. 
     In an embodiment, an exposure frame is the data sensed by the pixel array during the readout period  302  that occurs subsequent to a blanking period  316 . The emission of electromagnetic radiation is emitted during the blanking period  316 . In an embodiment, a portion of the emission of electromagnetic radiation overlaps the readout period  316 . The blanking period  316  occurs when optical black pixels of the pixel array are being read and the readout period  302  occurs when active pixels of the pixel array are being read. The blanking period  316  may overlap the readout period  302 . 
       FIGS. 6A and 6B  illustrate processes for recording an image frame. Multiple image frames may be strung together to generate a video stream. A single image frame may include data from multiple exposure frames, wherein an exposure frame is the data sensed by a pixel array subsequent to an emission of electromagnetic radiation.  FIG. 6A  illustrates a traditional process that is typically implemented with a color image sensor having a color filter array (CFA) for filtering out certain wavelengths of light per pixel.  FIG. 6B  is a process that is disclosed herein and can be implemented with a monochromatic “color agnostic” image sensor that is receptive to all wavelengths of electromagnetic radiation. 
     The process illustrated in  FIG. 6A  occurs from time t( 0 ) to time t( 1 ). The process begins with a white light emission  602  and sensing white light  604 . The image is processed and displayed at  606  based on the sensing at  604 . 
     The process illustrated in  FIG. 6B  occurs from time t( 0 ) to time t( 1 ). The process begins with an emission of green light  612  and sensing reflected electromagnetic radiation  614  subsequent to the emission of green light  612 . The process continues with an emission of red light  616  and sensing reflected electromagnetic radiation  618  subsequent to the emission of red light  616 . The process continues with an emission of blue light  620  and sensing reflected electromagnetic radiation  622  subsequent to the emission of blue light  620 . The process continues with one or more emissions of a laser mapping  624  pulsing scheme and sensing reflected electromagnetic energy  626  subsequent to each of the one or more emissions of the laser mapping  624  pulsing scheme. The image is processed and displayed at  628  based on each of the sensed reflected electromagnetic energy instances  614 ,  618 ,  622 , and  626 . 
     The process illustrated in  FIG. 6B  provides a higher resolution image and provides a means for generating an RGB image that further includes laser mapping data. When partitioned spectrums of light are used, (as in  FIG. 6B ) a sensor can be made sensitive to all wavelengths of electromagnetic energy. In the process illustrated in  FIG. 6B , the monochromatic pixel array is instructed that it is sensing electromagnetic energy from a predetermined partition of the full spectrum of electromagnetic energy in each cycle. Therefore, to form an image the sensor need only be cycled with a plurality of differing partitions from within the full spectrum of light. The final image is assembled based on the multiple cycles. Because the image from each color partition frame cycle has a higher resolution (compared with a CFA pixel array), the resultant image created when the partitioned light frames are combined also has a higher resolution. In other words, because each and every pixel within the array (instead of, at most, every second pixel in a sensor with a CFA) is sensing the magnitudes of energy for a given pulse and a given scene, just fractions of time apart, a higher resolution image is created for each scene. 
     As can be seen graphically in the embodiments illustrated in  FIGS. 6A and 6B  between times t( 0 ) and t( 1 ), the sensor for the partitioned spectrum system in  FIG. 6B  has cycled at least four times for every one of the full spectrum system in  FIG. 6A . In an embodiment, a display device (LCD panel) operates at 50-60 frames per second. In such an embodiment, the partitioned light system in  FIG. 6B  may operate at 200-240 frames per second to maintain the continuity and smoothness of the displayed video. In other embodiments, there may be different capture and display frame rates. Furthermore, the average capture rate could be any multiple of the display rate. 
     In an embodiment, it may be desired that not all partitions be represented equally within the system frame rate. In other words, not all light sources have to be pulsed with the same regularity so as to emphasize and de-emphasize aspects of the recorded scene as desired by the users. It should also be understood that non-visible and visible partitions of the electromagnetic spectrum may be pulsed together within a system with their respective data value being stitched into the video output as desired for display to a user. 
     An embodiment may comprise a pulse cycle pattern as follows: 
     i. Green pulse; 
     ii. Red pulse; 
     iii. Blue pulse; 
     iv. Green pulse; 
     v. Red pulse; 
     vi. Blue pulse; 
     vii. Laser mapping pulsing scheme; 
     viii. (Repeat) 
     As can be seen in the example, a laser mapping partition may be pulsed at a rate differing from the rates of the other partition pulses. This may be done to emphasize a certain aspect of the scene, with the laser mapping data simply being overlaid with the other data in the video output to make the desired emphasis. It should be noted that the addition of a laser mapping partition on top of the RED, GREEN, and BLUE partitions does not necessarily require the serialized system to operate at four times the rate of a full spectrum non-serial system because every partition does not have to be represented equally in the pulse pattern. As seen in the embodiment, the addition of a partition pulse that is represented less in a pulse pattern (laser mapping in the above example), would result in an increase of less than 20% of the cycling speed of the sensor to accommodate the irregular partition sampling. 
     The partition cycles may be divided so as to accommodate or approximate various imaging and video standards. In an embodiment, the partition cycles may comprise pulses of electromagnetic energy in the Red, Green, and Blue spectrum as follows as illustrated best in  FIGS. 7A-7D . In  FIG. 7A , the different light intensities have been achieved by modulating the light pulse width or duration within the working range shown by the vertical grey dashed lines. In  FIG. 7B , the different light intensities have been achieved by modulating the light power or the power of the electromagnetic emitter, which may be a laser or LED emitter, but keeping the pulse width or duration constant.  FIG. 7C  shows the case where both the light power and the light pulse width are being modulated, leading to greater flexibility. The partition cycles may use Cyan Magenta Yellow (CMY), infrared, ultraviolet, hyperspectral, and fluorescence using a non-visible pulse source mixed with visible pulse sources and any other color space required to produce an image or approximate a desired video standard that is currently known or yet to be developed. It should also be understood that a system may be able to switch between the color spaces on the fly to provide the desired image output quality. 
     In an embodiment using color spaces Green-Blue-Green-Red (as seen in  FIG. 7D ) it may be desirous to pulse the luminance components more often than the chrominance components because users are generally more sensitive to light magnitude differences than to light color differences. This principle can be exploited using a mono-chromatic sensor as illustrated in  FIG. 7D . In  FIG. 7D , green, which contains the most luminance information, may be pulsed more often or with more intensity in a (G-B-G-R-G-B-G-R . . . ) scheme to obtain the luminance data. Such a configuration would create a video stream that has perceptively more detail, without creating and transmitting unperceivable data. 
     In an embodiment, duplicating the pulse of a weaker partition may be used to produce an output that has been adjusted for the weaker pulse. For example, blue laser light is considered weak relative to the sensitivity of silicon-based pixels and is difficult to produce in comparison to the red or green light, and therefore may be pulsed more often during a frame cycle to compensate for the weakness of the light. These additional pulses may be done serially over time or by using multiple lasers that simultaneously pulse to produce the desired compensation effect. It should be noted that by pulsing during a blanking period (time during which the sensor is not reading out the pixel array), the sensor is insensitive to differences/mismatches between lasers of the same kind and simply accumulates the light for the desired output. In another embodiment, the maximum light pulse range may be different from frame to frame. This is shown in  FIG. 7E , where the light pulses are different from frame to frame. The sensor may be built to be able to program different blanking periods with a repeating pattern of two or three or four or n frames. In  FIG. 7E , four different light pulses are illustrated, and Pulse  1  may repeat for example after Pulse  4  and may have a pattern of four frames with different blanking periods. This technique can be used to place the most powerful partition on the smallest blanking period and therefore allow the weakest partition to have wider pulse on one of the next frames without the need of increasing the readout speed. The reconstructed frame can still have a regular pattern from frame to frame as it is constituted of many pulsed frames. 
       FIG. 8  is a schematic diagram of a process flow  800  to be implemented by a controller and/or monochrome image signal processor (ISP) for generating a video stream having RGB images with laser mapping data overlaid thereon. The process flow  800  results in images having increased dynamic range and spatial resolution. The image signal processor (ISP) chain may be assembled for the purpose of generating RGB image sequences from raw sensor data, yielded in the presence of the G-R-G-B-LaserMapping light pulsing scheme. In the process flow  800 , the first stage is concerned with making corrections to account for any non-idealities in the sensor technology for which it is most appropriate to work in the raw data domain. At the next stage, multiple exposure frames (for example, a green exposure frame  812   a , a red-blue exposure frame  812   b , and a laser mapping exposure frame  812   c ) are buffered because each final exposure frame derives data from multiple raw frames. The frame reconstruction at  814  proceeds by sampling data from a current exposure frame and buffered exposure frames (see  812   a ,  812   b , and/or  812   c ). The reconstruction process results in full color image frames in linear RGB color space that includes laser mapping image data. 
     The process flow  800  includes receiving data from an image sensor at  802 . Sensor correction calculations are performed at  804 . These sensor correction calculations can be used to determine statistics at  806  such as autoexposure settings and wide dynamic range settings. The process flow  800  continues and wide dynamic range fusion is processed at  808 . Wide dynamic range compression is processed at  810 . The wide dynamic range compression from  810  can be fed to generate the green exposure frame  812   a , the red-blue exposure frame  812 , and/or the laser mapping exposure frame  812   c . The process flow  800  continues and frame reconstruction is processed at  814  and then color correction is processed at  816 . The process flow  800  continues and an RGB (red-green-blue) image is converted to a YCbCr (luminance-chrominance blue-chrominance red) image at  818 . Edge enhancement is processed at  820  and then the YCbCr image is converted back to an RGB image at  822 . Scalars are processed at  824  and gamma is processed at  826 . The video is then exported at  828 . 
       FIG. 9  illustrates a process flow  900  for applying the super resolution (SR) and color motion artifact correction (CMAC) processes to image data. The super resolution algorithm uses data from multiple sequential exposure frames that are combined to generate individual image frames with increased spatial resolution. The generation of the individual image frames depends upon accurate motion detection within local regions of the multiple exposure frames. In some implementations, the luminance plane is the most critical plane for determining spatial resolution. If the luminance plane is the most critical plane, then only the adjacent luminance exposure frames are combined in an embodiment. In the case of red-green-blue pulsing according to an R-G-B-G pulsing schedule, only adjacent green exposure frames are combined to generate the individual image frames having higher spatial resolution. 
     With respect to the discussions regarding  FIG. 9 , the super resolution algorithm is applied in the context of Y-Cb-Cr light pulsing. YCbCr is a family of color spaces that can be used as part of the color image pipeline in video and digital photography systems. Y′ is the luminance component (may be referred to as the “luma” component) and represents the “black-and-white” or achromatic portion of the image. Cb is the blue-difference chrominance component (may be referred to as the “chroma” component) and Cr is the red-difference chrominance component. The chrominance components represent the color information in the image or video stream. Analog RGB image information can be converted into luminance and chrominance digital image information because human vision has finer spatial sensitivity to luminance (black-and-white) differences than chromatic (color) differences. Video and imaging systems can therefore store and transmit chromatic information at lower resolution and optimize perceived detail at a particular bandwidth. Y′ (with the prime notation) is distinguished from Y (without the prime notation), where Y is luminance and refers to light intensity. Y′CbCr color spaces are defined by a mathematical coordinate transformation from an associated RGB color space. If the underlying RGB color space is absolute, the Y′CbCr color space is an absolute color space as well. 
     The use of the super resolution algorithm as disclosed herein is not limited to any particular pulsing scheme and can be applied to YCbCr pulsing or to RGB pulsing. The super resolution algorithm may further be applied to hyperspectral and/or fluorescence image data. In an embodiment, the endoscopic imaging system disclosed herein pulses light to generate at least four types of captured frames. The captured exposure frames include a Y exposure frame that contains pure luminance information, a Cb exposure frame which contains a linear sum of Y and Cb data, and a Cr exposure frame which contains a linear sum of Y and Cr data. During frame reconstruction (i.e. color fusion). There may be one full color image frame in the YCbCr color space that is generated for each luminance exposure frame at the input. The luminance data may be combined with the chrominance data from the frame prior to and the frame following the luminance frame. Note that given this pulsing sequence, the position of the Cb frame with respect to the Y frame ping-pongs between the before and after slots for alternate Y cases, as does its complementary Cr component. Therefore, the data from each captured Cb or Cr chrominance frame may be utilized in two resultant full-color image frames. The minimum frame latency may be provided by performing the color fusion process during chrominance (Cb or Cr) frame capture. 
     The super resolution algorithm (see  906 ) enhances the resolution of an image frame by combining multiple exposure frames. Data from multiple sequential exposure frames is combined to increase the spatial resolution of the resultant image frame. The super resolution algorithm depends on accurate motion detection within local regions of the scene across the multiple exposure frames. The super resolution algorithm combines non-redundant information from the multiple exposure frames to generate a high-resolution image frame. The non-redundant information in the multiple exposure frames can be introduced by subpixel shifts between the multiple exposure frames. The subpixel shifts may occur due to uncontrolled motions by objects within the scene or by the imaging system itself. In an embodiment, the super resolution algorithm includes aligning the multiple exposure frames to pixel-level or subpixel-level accuracy and combining the multiple exposure frames into a high resolution image grid. There are numerous methods of applying a super resolution algorithm and any suitable method may be applied for combining the multiple exposure frames. 
     In an embodiment, the super resolution algorithm relies on the luminance plane to accurately detect motion within local regions of a scene captured by the multiple exposure frames. The luminance plane is the most critical for spatial resolution, and so the super resolution algorithm can be applied to luminance exposure frames in the case of Y-Cb-Cr light pulsing. In the case of R-G-B-G light pulsing, the super resolution algorithm can be applied to the green exposure frames. Embodiments of the disclosure are described in the context of the Y-Cb-Cr light pulsing scheme. However, it should be appreciated that the methods and systems described herein are not restricted to the Y-Cb-Cr pulsing scheme and can be applied to the R-G-B-G pulsing scheme. When the methods and systems are applied to the R-G-B-G pulsing scheme, the green exposure frame takes the place of the luminance exposure frame, the red exposure frame takes the place of the Cr exposure frame, and the blue exposure frame takes the place of the Cb exposure frame. 
     Referring again to the process flow  900  illustrated in  FIG. 9 , data from a sensor is input at  902 . Sensor correction  904  is performed on the sensor data. The super resolution (SR) and color motion artifact correction (CMAC) algorithms are implemented at  906 . The SR and CMAC processes  906  may be performed within the camera image signal processor on raw, captured sensor data. The SR and CMAC processes can be performed at  906  immediately after all digital sensor correction  904  processes are completed. The SR and CMAC processes  906  can be executed before the sensor data is fused into linear RGB or YCbCr space color images. Statistics can be exported at  908  to determine the appropriate autoexposure for the image. 
     A chrominance exposure frame  910   a  and a luminance exposure frame  910   b  are constructed. In an embodiment, a laser mapping exposure frame  910   c  is also constructed. The luminance exposure frame  910   b  is constructed based on the Y frames in arrival order. The chrominance exposure frames  910   a  are constructed based on the Cb and Cr frames in arrival order. The number of frames processed by the super resolution algorithm is an optional variable. The first-in-first-out depth of the luminance exposure frame  910   b  is normally odd and its size can be determined based on available processing, memory, memory-bandwidth, motion detection precision, or acceptable latency considerations. The color motion artifact correction process can be performed with the minimum first-in-first-out depth of three frames for Y and two frames for Cb and/or Cr. The super resolution algorithm may generate better resolution by the use of five luminance frames. 
     The super resolution process itself may involve combining data from multiple luminance exposure frames into a central super-resolved frame, which is stationary with respect to the luminance first-in-first-out (may be referred to as the RY buffer). For each of the non-central luminance buffers, an upscaled version is produced in which individual blocks are shifted according to their (x,y) motion vectors. Any pixels at the upscaled resolution that are not filled after shifting are left blank. 
     The image data is processed to implement frame reconstruction at  912  and edge enhancement at  914 . The YCbCr image is converted to an RGB image at  916 . Statistics on the RGB image can be exported at  918  to determine appropriate white balance. The appropriate white balance is applied at  920  and entered into the color correction matric at  922 . Scalars  924  and gamma  926  are determined and the video is exported out at  928 . The process flow  900  can be implemented in the camera image signal processor in real-time while image data is captured and received from the sensor (see  902 ). 
     During frame reconstruction  912 , there may be one full color image frame in YCbCr space generated for each luminance exposure frame. The data captured in the luminance exposure frame may be combined with data from chrominance exposure frames captured before and after the luminance exposure frame. Given this pulsing sequence, the position of the Cb exposure frame with respect to the luminance exposure frame may be adjusted to occur before or after the luminance exposure frame for alternate luminance cases. The same is true for the Cr exposure frame with respect to the luminance exposure frame. Therefore, the data from each captured Cb or Cr exposure frame is used in two resultant full color images. The minimum frame latency may be provided by performing the frame reconstruction  912  process during the Cb and Cr frame capture. 
     In an embodiment, two frame first-in-first-out (FIFO) flows are constructed. One FIFO is constructed for luminance exposure frames in arrival order and another FIFO is constructed for Cb exposure frames and Cr exposure frames. The number of frames to use for the super resolution (see  906 ) process is an optional variable. The luminance FIFO depth may be odd, and its size may be determined by the available processing, memory, or memory bandwidth, or by motion detection precision or acceptable latency considerations. The color motion artifact correction (CMAC) at  906  may be performed with the minimum FIFO depth of three luminance exposure frames and two chrominance exposure frames. For the super resolution algorithm, the use of five luminance exposure frames results in improved resolution. On luminance exposure frames, the current object frame is the central in the luminance FIFO. On chrominance exposure frames the two chrominance exposure frames that flank the central luminance exposure frame are adjusted to line up motion to the central luminance exposure frame. 
       FIG. 10  is a schematic of an example pixel array  1000  that may be used to implement the process flow  900  illustrated in  FIG. 9 . The pixel array  1000  includes a block of luminance pixels  1004  for generating data for a Y luminance exposure frame. The pixel array  1000  includes RY pixels  1002  framing the block of luminance pixels  1004 . The RY pixels  1002  are buffered first-in-first-out pixels. 
     On a luminance exposure frame, the current object frame is the central block of luminance pixels  1004  in the first-in-first-out. On chrominance frames, the Cb and Cr frames flank the central block of luminance pixels  1004 . This is adjusted to line up motion to the central block of luminance pixels  1004  to detect motion. 
     The super resolution and CMAC algorithms (see  906 ) rely on motion detection. In an embodiment, a motion detection method includes block matching which provides x and y motion vectors for small, independent blocks of pixels of configurable dimensions. There are other motion detection algorithms that may be used in other implementations. Bock matching offers advantages for simplicity of implementation and particularly for real time processing in hardware. In an embodiment, a two-stage match process is described which provides for a super resolved frame with two times the pixel count in the x and y directions. Further stages may be added to increase the pixel count further. However, many more buffered frames and computations would be required to make this worthwhile. In an embodiment, in addition to the raw, buffered, luminance exposure frames disposed in the middle of the luminance FIFO (referred to as frame RY pixels)  1002 , three two-times upscaled versions of the middle block of luminance pixels  1004  are created. The middle block of luminance pixels  1004  may be upscaled using bilinear interpolation (referred to as buffer BL). In an additional exposure frame, the block of luminance pixels  1004  may be upscaled using bicubic interpolation (referred to as buffer BC). In an additional exposure frame, the block of luminance pixels  1004  may be upscaled with no interpolation such that the upscaled frame includes only zeros in the place of empty pixels (referred to as NI). The bilinear interpolation may be used in the block matching method. The no interpolation forms the baseline for the super resolved frame. The bicubic interpolation may serve as a fallback pixel source for unfilled pixels within the super resolved frame. 
       FIG. 11  illustrates a schematic of a pixel array  1100  with luminance frame pixels  1104  disbursed within pixels frame BL  1102 . For each luminance exposure frame in the buffer, except for the frame RY pixels  1002 , the pixel array may be segmented into square blocks of some dimension as illustrated in  FIG. 10 . Each block is shifted around, one pixel at a time, in both x and y directions, within some defined range of shifts in both positive and negative directions. For each pixel location, the pixel data may be compared to the equivalent block sitting in that location with the object frame RY pixels  1002 . The x and y shifts encountered for the best match position become the recorded Cartesian motion coordinates for all pixels within the block. This process is depicted in  FIG. 11 . 
     In the pixel array  1100 , for each luminance exposure frame in the buffer, except for RY, the pixel array  1000  shown in  FIG. 10  may be segmented into square blocks of some dimension, (e.g. 4×4). Each block is shifted around, one pixel at a time, in both x and y, within some defined range of shifts in both positive and negative directions (e.g. +/−3 pixels). For each location within the pixel array, a pixel may be compared to an equivalent block sitting in that location with the object frame, RY. The x and y shifts encountered for the best match position become the recorded Cartesian motion coordinates for all pixels within the pixel array  1100 . There are various ways to make the comparison and a relatively convenient metric is the modulus of the pixel differences, (i.e. between the stationary pixel in RY and the corresponding pixel in the block under study), summed over all pixels in the pixel array  1100 . The best match may be taken as the minimum of this value. It can also be recorded for each block as a matching quality metric, which may be used to arbitrate between competing pixels during the spatial resolution process. 
     There are various ways to make this comparison. In an embodiment, a metric is calculated based on the modulus of the pixel differences, i.e., between the stationary pixel in the frame RY pixels  1002  and the corresponding pixels in the block under study, summed over all pixels in the block. The best match may be taken as the minimum of this value. The best match can be recorded for each block as a matching quality metric that may be used to arbitrate between competing pixels during the super resolution algorithm (see  906 ). Alternatively, the minimum sum of squared differences may be used as the matching matric. At this stage, each pixel within non-RY luminance frames has a motion estimate that is quantized at the captured resolution. In an implementation where 2× resolution is sought, the method includes comparing a block of pixels within the non-RY frames to the BL buffer. This begins from the best shifted position according to the recorded motion vectors. Shifts are performed by shifting one-half pixel in the positive and negative directions to give a total of nine possible positions. A half pixel in the luminance frame under study is one whole pixel with respect to BL. Of those nine possible pixel positions, the best match is again determined, and the recorded motion vector is adjusted accordingly. If the motion vector at this stage has a half integer component, then the motion vector has the potential to enhance the resolution of the resultant image frame. 
     Motion vectors for the two luminance exposure frames flanking RY may be saved for the CMAC process. The CMAC process may be performed during the chrominance exposure frames. The super resolution process itself may include combining data from multiple exposure frames in a central super resolved frame. The central super resolved frame is stationary with respect to the RY buffer. For each of the non-central luminance buffers a 2× upscaled version is generated in which the individual blocks have been shifted according to their (x,y) motion vectors. Any pixels at the 2× resolution that are not filled after shifting are left blank. 
     The basis of the super resolved frame is the NI buffer which is the upscaled version of RY with no interpolation. Three of every four pixels in NI may be initially blank. The primary objective may be to fill the pixels with data from the upscaled and shifted luminance buffers. One approach is to scan the pixels for the first match for each empty pixel. At the end, any pixels still blank may be filled in from the BC buffer. Another approach is to assess possible candidates and select the best candidate based on a parameter that has been logged as a motion estimate quality metric. An example of a motion estimate quality metric is the minimum sum of absolute differences for the originating block or some derivative thereof. Another approach is to combine all candidates in some way, e.g., average the candidates or perform a weighted average according to a quality parameter. In such an approach, even non-zero pixels in NI can be substituted. The benefit of such an approach is that in addition to enhancing the resolution, the net signal to noise ratio is also improved. Candidates with notably poor quality values can also be rejected. 
     Each pixel within non-RY, luminance frames, has a motion estimate that is quantized at the captured resolution. If X2 super resolution is sought, the next stage involves, for block of pixels within the non-RY frames, comparing to the BL buffer instead of the RY buffer. Starting from the best shifted position (according to the recorded motion vectors). Shifts can be performed by positive and negative half-pixel, giving a total of nine possible positions as shown in  FIG. 11 . Of those nine possible pixel positions, the best match is again determined, and the recorded motion vector is adjusted accordingly. 
     Motion vectors for the luminance frames flanking RY frames may be saved for the color motion artifact correction (CMAC) process which occurs during the C frames. The basis of the super-resolved frame is the NI buffer which is the upscaled version of RY with no interpolation. Three out of every four pixels in NI may be initially blank, and the primary objective is to fill them with data from the upscaled &amp; shifted luminance buffers. At the end, any pixels which are still blank may be filled in from the BC buffer which is the bicubic interpolated version of the central luminance frame. A more sophisticated approach to filling may be to assess all possible candidates and choose the best one based on some parameter that has been logged as a motion estimate quality metric. An example of such a metric could be the minimum sum of absolute differences for the originating block, or some derivative thereof. This requires at least one additional frame buffer per luminance frame. Alternatively, all candidates can be combined in some way, e.g. as an average which can be weighted according to a quality parameter. Candidates with notably poor quality values can also be rejected altogether. 
       FIG. 12  illustrates the issue of significant motion from frame to frame with framewise color modulation.  FIG. 12  illustrates an example in which a ball is traveling through the scene at a quicker rate than the rate of capture for the Cb exposure frame, the Y exposure frame, the Cr exposure frame, and the laser mapping exposure frame. The ball is moving on a trajectory across the scene during capture that results in different positions for the Y, Cb, Cr, and laser mapping exposure frames. The basis of the color motion artifact correction is to utilize the relative motion estimation for adjacent luminance (Y) frames to predict the motion that occurred for the intermediate Cb, Cr, and laser mapping exposure frames relative to the luminance frame. 
     In an embodiment, the motion vectors for adjacent luminance frames are assessed and divided by two. This assumes that any motion that has occurred from luminance frame to luminance frame is linear. If motion estimation is available for three or more luminance frames in addition to the object frame (RY), then bicubic interpolation may be employed for a more precise interpolation. The pixel shifting can take place either at the original or the doubled resolution following a bicubic upscale. Either way, after shifting, there are many void locations with various random shapes and sizes which may be filled in to ensure good image quality. 
     The application of motion information can be different for color motion artifact correction (CMAC) compared with super resolution. Super resolution uses a bicubic upscaled version of RY as a default, so the worst case is that a pixel void is filled by interpolation using the sixteen closest neighbors in the correct motion frame. For CMAC, there may be no predicting the distance of the nearest filled neighbors such that the known information is limited to the original block search distance divided by two. Some means of interpolation are required to fill in the holes. One way to do this is for each missing pixel, find the distance to the closest filled pixel in the positive and negative x and y directions, and then fill with an average level that has been weighted according to the reciprocal of each distance. 
       FIG. 13  is a schematic diagram of a pattern reconstruction process. The example pattern illustrated in  FIG. 13  includes Red, Green, Blue, and Laser Mapping pulses of light that each last a duration of T 1 . It should be appreciated that the pattern reconstruction process illustrated in  FIG. 13  can also be applied to a Y-Cb-Cr-LaserMapping pulsing scheme. In various embodiments, the pulses of light may be of the same duration or of differing durations. The Red, Green, Blue, and Laser mapping exposure frames are combined to generate an RGB image with laser mapping imaging data overlaid thereon. A single image frame comprising a red exposure frame, a green exposure frame, a blue exposure frame, and a laser mapping exposure frame requires a time period of 4*T 1  to be generated. The time durations shown in  FIG. 13  are illustrative only and may vary for different implementations. In other embodiments, different pulsing schemes may be employed. For example, embodiments may be based on the timing of each color component or frame (T 1 ) and the reconstructed frame having a period twice that of the incoming color frame (2×T 1 ). Different frames within the sequence may have different frame periods and the average capture rate could be any multiple of the final frame rate. 
     In an embodiment, the dynamic range of the system is increased by varying the pixel sensitivities of pixels within the pixel array of the image sensor. Some pixels may sense reflected electromagnetic radiation at a first sensitivity level, other pixels may sense reflected electromagnetic radiation at a second sensitivity level, and so forth. The different pixel sensitivities may be combined to increase the dynamic range provided by the pixel configuration of the image sensor. In an embodiment, adjacent pixels are set at different sensitivities such that each cycle includes data produced by pixels that are more and less sensitive with respect to each other. The dynamic range is increased when a plurality of sensitivities are recorded in a single cycle of the pixel array. In an embodiment, wide dynamic range can be achieved by having multiple global TX, each TX firing only on a different set of pixels. For example, in global mode, a global TX 1  signal is firing a set  1  of pixels, a global TX 2  signal is firing a set  2  of pixel, a global TXn signal is firing a set n of pixels, and so forth. 
       FIGS. 14A-14C  each illustrate a light source  1400  having a plurality of emitters. The emitters include a first emitter  1402 , a second emitter  1404 , and a third emitter  1406 . Additional emitters may be included, as discussed further below. The emitters  1402 ,  1404 , and  1406  may include one or more laser emitters that emit light having different wavelengths. For example, the first emitter  1402  may emit a wavelength that is consistent with a blue laser, the second emitter  1404  may emit a wavelength that is consistent with a green laser, and the third emitter  1406  may emit a wavelength that is consistent with a red laser. For example, the first emitter  1402  may include one or more blue lasers, the second emitter  1404  may include one or more green lasers, and the third emitter  1406  may include one or more red lasers. The emitters  1402 ,  1404 ,  1406  emit laser beams toward a collection region  1408 , which may be the location of a waveguide, lens, or other optical component for collecting and/or providing light to a waveguide, such as the jumper waveguide  206  or lumen waveguide  210  of  FIG. 2 . 
     In an implementation, the emitters  1402 ,  1404 , and  1406  emit hyperspectral wavelengths of electromagnetic radiation. Certain hyperspectral wavelengths may pierce through tissue and enable a medical practitioner to “see through” tissues in the foreground to identify chemical processes, structures, compounds, biological processes, and so forth that are located behind the tissues in the foreground. The hyperspectral wavelengths may be specifically selected to identify a specific disease, tissue condition, biological process, chemical process, type of tissue, and so forth that is known to have a certain spectral response. 
     In an implementation where a patient has been administered a reagent or dye to aid in the identification of certain tissues, structures, chemical reactions, biological processes, and so forth, the emitters  1402 ,  1404 , and  1406  may emit wavelength(s) for fluorescing the reagents or dyes. Such wavelength(s) may be determined based on the reagents or dyes administered to the patient. In such an embodiment, the emitters may need to be highly precise for emitting desired wavelength(s) to fluoresce or activate certain reagents or dyes. 
     In an implementation, the emitters  1402 ,  1404 , and  1406  emit a laser mapping pattern for mapping a topology of a scene and/or for calculating dimensions and distances between objects in the scene. In an embodiment, the endoscopic imaging system is used in conjunction with multiple tools such as scalpels, retractors, forceps, and so forth. In such an embodiment, each of the emitters  1402 ,  1404 , and  1406  may emit a laser mapping pattern such that a laser mapping pattern is projected on to each tool individually. In such an embodiment, the laser mapping data for each of the tools can be analyzed to identify distances between the tools and other objects in the scene. 
     In the embodiment of  FIG. 14B , the emitters  1402 ,  1404 ,  1406  each deliver laser light to the collection region  1408  at different angles. The variation in angle can lead to variations where electromagnetic energy is located in an output waveguide. For example, if the light passes immediately into a fiber bundle (glass or plastic) at the collection region  1408 , the varying angles may cause different amounts of light to enter different fibers. For example, the angle may result in intensity variations across the collection region  1408 . Furthermore, light from the different emitters may not be homogenously mixed so some fibers may receive different amounts of light of different colors. Variation in the color or intensity of light in different fibers can lead to non-optimal illumination of a scene. For example, variations in delivered light or light intensities may result at the scene and captured images. 
     In one embodiment, an intervening optical element may be placed between a fiber bundle and the emitters  1402 ,  1404 ,  1406  to mix the different colors (wavelengths) of light before entry into the fibers or other waveguide. Example intervening optical elements include a diffuser, mixing rod, one or more lenses, or other optical components that mix the light so that a given fiber receive a same amount of each color (wavelength). For example, each fiber in the fiber bundle may have a same color. This mixing may lead to the same color in each fiber but may, in some embodiments, still result in different total brightness delivered to different fibers. In one embodiment, the intervening optical element may also spread out or even out the light over the collection region so that each fiber carries the same total amount of light (e.g., the light may be spread out in a top hat profile). A diffuser or mixing rod may lead to loss of light. 
     Although the collection region  1408  is represented as a physical component in  FIG. 14A , the collection region  1408  may simply be a region where light from the emitters  1402 ,  1404 , and  1406  is delivered. In some cases, the collection region  1408  may include an optical component such as a diffuser, mixing rod, lens, or any other intervening optical component between the emitters  1402 ,  1404 ,  1406  and an output waveguide. 
       FIG. 14C  illustrates an embodiment of a light source  1400  with emitters  1402 ,  1404 ,  1406  that provide light to the collection region  1408  at the same or substantially same angle. The light is provided at an angle substantially perpendicular to the collection region  1408 . The light source  1400  includes a plurality of dichroic mirrors including a first dichroic mirror  1410 , a second dichroic mirror  1412 , and a third dichroic mirror  1414 . The dichroic mirrors  1410 ,  1412 ,  1414  include mirrors that reflect a first wavelength of light but transmit (or are transparent to) a second wavelength of light. For example, the third dichroic mirror  1414  may reflect blue laser light provided by the third emitter, while being transparent to the red and green light provided by the first emitter  1402  and the second emitter  1404 , respectively. The second dichroic mirror  1412  may be transparent to red light from the first emitter  1402 , but reflective to green light from the second emitter  1404 . If other colors or wavelengths are included dichroic mirrors may be selected to reflect light corresponding to at least one emitter and be transparent to other emitters. For example, the third dichroic mirror  1414  reflect the light form the third emitter  1406  but is to emitters “behind” it, such as the first emitter  1402  and the second emitter  1404 . In embodiments where tens or hundreds of emitters are present, each dichroic mirror may be reflective to a corresponding emitter and emitters in front of it while being transparent to emitters behind it. This may allow for tens or hundreds of emitters to emit electromagnetic energy to the collection region  1408  at a substantially same angle. 
     Because the dichroic mirrors allow other wavelengths to transmit or pass through, each of the wavelengths may arrive at the collection region  1408  from a same angle and/or with the same center or focal point. Providing light from the same angle and/or same focal/center point can significantly improve reception and color mixing at the collection region  1408 . For example, a specific fiber may receive the different colors in the same proportions they were transmitted/reflected by the emitters  1402 ,  1404 ,  1406  and mirrors  1410 ,  1412 ,  1414 . Light mixing may be significantly improved at the collection region compared to the embodiment of  FIG. 14B . In one embodiment, any optical components discussed herein may be used at the collection region  1408  to collect light prior to providing it to a fiber or fiber bundle. 
       FIG. 14C  illustrates an embodiment of a light source  1400  with emitters  1402 ,  1404 ,  1406  that also provide light to the collection region  1408  at the same or substantially same angle. However, the light incident on the collection region  1408  is offset from being perpendicular. Angle  1416  indicates the angle offset from perpendicular. In one embodiment, the laser emitters  1402 ,  1404 ,  1406  may have cross sectional intensity profiles that are Gaussian. As discussed previously, improved distribution of light energy between fibers may be accomplished by creating a more flat or top-hat shaped intensity profile. In one embodiment, as the angle  1416  is increased, the intensity across the collection region  1408  approaches a top hat profile. For example, a top-hat profile may be approximated even with a non-flat output beam by increasing the angle  1416  until the profile is sufficiently flat. The top hat profile may also be accomplished using one or more lenses, diffusers, mixing rods, or any other intervening optical component between the emitters  1402 ,  1404 ,  1406  and an output waveguide, fiber, or fiber optic bundle. 
       FIG. 15  is a schematic diagram illustrating a single optical fiber  1502  outputting via a diffuser  1504  at an output. In one embodiment, the optical fiber  1502  has a diameter of 500 microns, a numerical aperture of 0.65, and emits a light cone  1506  of about 70 or 80 degrees without a diffuser  1504 . With the diffuser  1504 , the light cone  1506  may have an angle of about 110 or 120 degrees. The light cone  1506  may be a majority of where all light goes and is evenly distributed. The diffuser  1504  may allow for more even distribution of electromagnetic energy of a scene observed by an image sensor. 
     In one embodiment, the lumen waveguide  210  includes a single plastic or glass optical fiber of about 500 microns. The plastic fiber may be low cost, but the width may allow the fiber to carry a sufficient amount of light to a scene, with coupling, diffusion, or other losses. For example, smaller fibers may not be able to carry as much light or power as a larger fiber. The lumen waveguide  210  may include a single or a plurality of optical fibers. The lumen waveguide  210  may receive light directly from the light source or via a jumper waveguide. A diffuser may be used to broaden the light output  206  for a desired field of view of the image sensor  214  or other optical components. 
     Although three emitters are shown in  FIGS. 14A-14C , emitters numbering from one into the hundreds or more may be used in some embodiments. The emitters may have different wavelengths or spectrums of light that they emit, and which may be used to contiguously cover a desired portion of the electromagnetic spectrum (e.g., the visible spectrum as well as infrared and ultraviolet spectrums). The emitters may be configured to emit visible light such as red light, green light, and blue light, and may further be configured to emit hyperspectral emissions of electromagnetic radiation, fluorescence excitation wavelengths for fluorescing a reagent, and/or laser mapping patterns for calculating parameters and distances between objects in a scene. 
       FIG. 16  illustrates a portion of the electromagnetic spectrum  1600  divided into twenty different sub-spectrums. The number of sub-spectrums is illustrative only. In at least one embodiment, the spectrum  1600  may be divided into hundreds of sub-spectrums, each with a small waveband. The spectrum may extend from the infrared spectrum  1602 , through the visible spectrum  1604 , and into the ultraviolet spectrum  1606 . The sub-spectrums each have a waveband  1608  that covers a portion of the spectrum  1600 . Each waveband may be defined by an upper wavelength and a lower wavelength. 
     Hyperspectral imaging includes imaging information from across the electromagnetic spectrum  1600 . A hyperspectral pulse of electromagnetic radiation may include a plurality of sub-pulses spanning one or more portions of the electromagnetic spectrum  1600  or the entirety of the electromagnetic spectrum  1600 . A hyperspectral pulse of electromagnetic radiation may include a single partition of wavelengths of electromagnetic radiation. A resulting hyperspectral exposure frame includes information sensed by the pixel array subsequent to a hyperspectral pulse of electromagnetic radiation. Therefore, a hyperspectral exposure frame may include data for any suitable partition of the electromagnetic spectrum  1600  and may include multiple exposure frames for multiple partitions of the electromagnetic spectrum  1600 . In an embodiment, a hyperspectral exposure frame includes multiple hyperspectral exposure frames such that the combined hyperspectral exposure frame comprises data for the entirety of the electromagnetic spectrum  1600 . 
     In one embodiment, at least one emitter (such as a laser emitter) is included in a light source (such as the light sources  202 ,  1700 ) for each sub-spectrum to provide complete and contiguous coverage of the whole spectrum  1600 . For example, a light source for providing coverage of the illustrated sub-spectrums may include at least 20 different emitters, at least one for each sub-spectrum. In one embodiment, each emitter covers a spectrum covering 40 nanometers. For example, one emitter may emit light within a waveband from 500 nm to 540 nm while another emitter may emit light within a waveband from 540 nm to 580 nm. In another embodiment, emitters may cover other sizes of wavebands, depending on the types of emitters available or the imaging needs. For example, a plurality of emitters may include a first emitter that covers a waveband from 500 to 540 nm, a second emitter that covers a waveband from 540 nm to 640 nm, and a third emitter that covers a waveband from 640 nm to 650 nm. Each emitter may cover a different slice of the electromagnetic spectrum ranging from far infrared, mid infrared, near infrared, visible light, near ultraviolet and/or extreme ultraviolet. In some cases, a plurality of emitters of the same type or wavelength may be included to provide sufficient output power for imaging. The number of emitters needed for a specific waveband may depend on the sensitivity of a monochrome sensor to the waveband and/or the power output capability of emitters in that waveband. 
     The waveband widths and coverage provided by the emitters may be selected to provide any desired combination of spectrums. For example, contiguous coverage of a spectrum using very small waveband widths (e.g., 10 nm or less) may allow for highly selective hyperspectral and/or fluorescence imaging. The waveband widths may allow for selectively emitting the excitation wavelength(s) for one or more particular fluorescent reagents. Additionally, the waveband widths may allow for selectively emitting certain partitions of hyperspectral electromagnetic radiation for identifying specific structures, chemical processes, tissues, biological processes, and so forth. Because the wavelengths come from emitters which can be selectively activated, extreme flexibility for fluorescing one or more specific fluorescent reagents during an examination can be achieved. Additionally, extreme flexibility for identifying one or more objects or processes by way of hyperspectral imaging can be achieved. Thus, much more fluorescence and/or hyperspectral information may be achieved in less time and within a single examination which would have required multiple examinations, delays because of the administration of dyes or stains, or the like. 
       FIG. 17  is a schematic diagram illustrating a timing diagram  1700  for emission and readout for generating an image. The solid line represents readout (peaks  1702 ) and blanking periods (valleys) for capturing a series of exposure frames  1704 - 1714 . The series of exposure frames  1704 - 1714  may include a repeating series of exposure frames which may be used for generating laser mapping, hyperspectral, and/or fluorescence data that may be overlaid on an RGB video stream. In an embodiment, a single image frame comprises information from multiple exposure frames, wherein one exposure frame includes red image data, another exposure frame includes green image data, and another exposure frame includes blue image data. Additionally, the single image frame may include one or more of hyperspectral image data, fluorescence image data, and laser mapping data. The multiple exposure frames are combined to produce the single image frame. The single image frame is an RGB image with hyperspectral imaging data. The series of exposure frames include a first exposure frame  1704 , a second exposure frame  1706 , a third exposure frame  1708 , a fourth exposure frame  1710 , a fifth exposure frame  1712 , and an Nth exposure frame  1726 . 
     Additionally, the hyperspectral image data, the fluorescence image data, and the laser mapping data can be used in combination to identify critical tissues or structures and further to measure the dimensions of those critical tissues or structures. For example, the hyperspectral image data may be provided to a corresponding system to identify certain critical structures in a body such as a nerve, ureter, blood vessel, cancerous tissue, and so forth. The location and identification of the critical structures may be received from the corresponding system and may further be used to generate topology of the critical structures using the laser mapping data. For example, a corresponding system determines the location of a cancerous tumor based on hyperspectral imaging data. Because the location of the cancerous tumor is known based on the hyperspectral imaging data, the topology and distances of the cancerous tumor may then be calculated based on laser mapping data. This example may also apply when a cancerous tumor or other structure is identified based on fluorescence imaging data. 
     In one embodiment, each exposure frame is generated based on at least one pulse of electromagnetic energy. The pulse of electromagnetic energy is reflected and detected by an image sensor and then read out in a subsequent readout ( 1702 ). Thus, each blanking period and readout results in an exposure frame for a specific spectrum of electromagnetic energy. For example, the first exposure frame  1704  may be generated based on a spectrum of a first one or more pulses  1716 , a second exposure frame  1706  may be generated based on a spectrum of a second one or more pulses  1718 , a third exposure frame  1708  may be generated based on a spectrum of a third one or more pulses  1720 , a fourth exposure frame  1710  may be generated based on a spectrum of a fourth one or more pulses  1722 , a fifth exposure frame  1712  may be generated based on a spectrum of a fifth one or more pulses  1724 , and an Nth exposure frame  1726  may be generated based on a spectrum of an Nth one or more pulses  1726 . 
     The pulses  1716 - 1726  may include energy from a single emitter or from a combination of two or more emitters. For example, the spectrum included in a single readout period or within the plurality of exposure frames  1704 - 1714  may be selected for a desired examination or detection of a specific tissue or condition. According to one embodiment, one or more pulses may include visible spectrum light for generating an RGB or black and white image while one or more additional pulses are emitted to sense a spectral response to a hyperspectral wavelength of electromagnetic radiation. For example, pulse  1716  may include red light, pulse  1718  may include blue light, and pulse  1720  may include green light while the remaining pulses  1722 - 1726  may include wavelengths and spectrums for detecting a specific tissue type, fluorescing a reagent, and/or mapping the topology of the scene. As a further example, pulses for a single readout period include a spectrum generated from multiple different emitters (e.g., different slices of the electromagnetic spectrum) that can be used to detect a specific tissue type. For example, if the combination of wavelengths results in a pixel having a value exceeding or falling below a threshold, that pixel may be classified as corresponding to a specific type of tissue. Each frame may be used to further narrow the type of tissue that is present at that pixel (e.g., and each pixel in the image) to provide a very specific classification of the tissue and/or a state of the tissue (diseased/healthy) based on a spectral response of the tissue and/or whether a fluorescent reagent is present at the tissue. 
     The plurality of frames  1704 - 1714  is shown having varying lengths in readout periods and pulses having different lengths or intensities. The blanking period, pulse length or intensity, or the like may be selected based on the sensitivity of a monochromatic sensor to the specific wavelength, the power output capability of the emitter(s), and/or the carrying capacity of the waveguide. 
     In one embodiment, dual image sensors may be used to obtain three-dimensional images or video feeds. A three-dimensional examination may allow for improved understanding of a three-dimensional structure of the examined region as well as a mapping of the different tissue or material types within the region. 
     In an example implementation, a fluorescent reagent is provided to a patient, and the fluorescent reagent is configured to adhere to cancerous cells. The fluorescent reagent is known to fluoresce when radiated with a specific partition of electromagnetic radiation. The relaxation wavelength of the fluorescent reagent is also known. In the example implementation, the patient is imaged with an endoscopic imaging system as discussed herein. The endoscopic imaging system pulses partitions of red, green, and blue wavelengths of light to generate an RGB video stream of the interior of the patient&#39;s body. Additionally, the endoscopic imaging system pulses the excitation wavelength of electromagnetic radiation for the fluorescent reagent that was administered to the patient. In the example, the patient has cancerous cells and the fluorescent reagent has adhered to the cancerous cells. When the endoscopic imaging system pulses the excitation wavelength for the fluorescent reagent, the fluorescent reagent will fluoresce and emit a relaxation wavelength. If the cancerous cells are present in the scene being imaged by the endoscopic imaging system, then the fluorescent reagent will also be present in the scene and will emit its relaxation wavelength after fluorescing due to the emission of the excitation wavelength. The endoscopic imaging system senses the relaxation wavelength of the fluorescent reagent and thereby senses the presence of the fluorescent reagent in the scene. Because the fluorescent reagent is known to adhere to cancerous cells, the presence of the fluorescent reagent further indicates the presence of cancerous cells within the scene. The endoscopic imaging system thereby identifies the location of cancerous cells within the scene. The endoscopic imaging system may further emit a laser mapping pulsing scheme for generating a topology of the scene and calculating dimensions for objects within the scene. The location of the cancerous cells (as identified by the fluorescence imaging data) may be combined with the topology and dimensions information calculated based on the laser mapping data. Therefore, the precise location, size, dimensions, and topology of the cancerous cells may be identified. This information may be provided to a medical practitioner to aid in excising the cancerous cells. Additionally, this information may be provided to a robotic surgical system to enable the surgical system to excise the cancerous cells. 
     In a further example implementation, a patient is imaged with an endoscopic imaging system to identify quantitative diagnostic information about the patient&#39;s tissue pathology. In the example, the patient is suspected or known to suffer from a disease that can be tracked with hyperspectral imaging to observe the progression of the disease in the patient&#39;s tissue. The endoscopic imaging system pulses partitions of red, green, and blue wavelengths of light to generate an RGB video stream of the interior of the patient&#39;s body. Additionally, the endoscopic imaging system pulses one or more hyperspectral wavelengths of light that permit the system to “see through” some tissues and generate imaging of the tissue that is affected by the disease. The endoscopic imaging system senses the reflected hyperspectral electromagnetic radiation to generate hyperspectral imaging data of the diseased tissue, and thereby identifies the location of the diseased tissue within the patient&#39;s body. The endoscopic imaging system may further emit a laser mapping pulsing scheme for generating a topology of the scene and calculating dimensions of objects within the scene. The location of the diseased tissue (as identified by the hyperspectral imaging data) may be combined with the topology and dimensions information that is calculated with the laser mapping data. Therefore, the precise location, size, dimensions, and topology of the diseased tissue can be identified. This information may be provided to a medical practitioner to aid in excising, imaging, or studying the diseased tissue. Additionally, this information may be provided to a robotic surgical system to enable the surgical system to excise the diseased tissue. 
       FIG. 18  is a schematic diagram of an imaging system  1800  having a single cut filter. The system  1800  includes an endoscope  1806  or other suitable imaging device having a light source  1808  for use in a light deficient environment. The endoscope  1806  includes an image sensor  1804  and a filter  1802  for filtering out unwanted wavelengths of light or other electromagnetic radiation before reaching the image sensor  1804 . The light source  1808  transmits light that may illuminate the surface  1812  in a light deficient environment such as a body cavity. The light  1810  is reflected off the surface  1812  and passes through the filter  1802  before hitting the image sensor  1804 . 
     The filter  1802  may be used in an implementation where a fluorescent reagent or dye has been administered. In such an embodiment, the light source  1808  emits the excitation wavelength for fluorescing the fluorescent reagent or dye. Commonly, the relaxation wavelength emitted by the fluorescent reagent or dye will be of a different wavelength than the excitation wavelength. The filter  1802  may be selected to filter out the excitation wavelength and permit only the relaxation wavelength to pass through the filter and be sensed by the image sensor  1804 . 
     In one embodiment, the filter  1802  is configured to filter out an excitation wavelength of electromagnetic radiation that causes a reagent or dye to fluoresce such that only the expected relaxation wavelength of the fluoresced reagent or dye is permitted to pass through the filter  1802  and reach the image sensor  1804 . In an embodiment, the filter  1802  filters out at least a fluorescent reagent excitation wavelength between 770 nm and 790 nm. In an embodiment, the filter  1802  filters out at least a fluorescent reagent excitation wavelength between 795 nm and 815 nm. In an embodiment, the filter  1802  filters out at least a fluorescent reagent excitation wavelength between 770 nm and 790 nm and between 795 nm and 815 nm. In these embodiments, the filter  1802  filters out the excitation wavelength of the reagent and permits only the relaxation wavelength of the fluoresced reagent to be read by the image sensor  1804 . The image sensor  1804  may be a wavelength-agnostic image sensor and the filter  1802  may be configured to permit the image sensor  1804  to only receive the relaxation wavelength of the fluoresced reagent and not receive the emitted excitation wavelength for the reagent. The data determined by the image sensor  1804  may then indicate a presence of a critical body structure, tissue, biological process, or chemical process as determined by a location of the reagent or dye. 
     The filter  1802  may further be used in an implementation where a fluorescent reagent or dye has not been administered. The filter  1802  may be selected to permit wavelengths corresponding to a desired spectral response to pass through and be read by the image sensor  1804 . The image sensor  1804  may be a monochromatic image sensor such that pixels of the captured image that exceed a threshold or fall below a threshold may be characterized as corresponding to a certain spectral response or fluorescence emission. The spectral response or fluorescence emission, as determined by the pixels captured by the image sensor  1804 , may indicate the presence of a certain body tissue or structure, a certain condition, a certain chemical process, and so forth. 
       FIG. 19  is a schematic diagram of an imaging system  1900  having multiple cut filters. The system  1900  includes an endoscope  1906  or other suitable imaging device having a light source  1908  for use in a light deficient environment. The endoscope  1906  includes an image sensor  1904  and two filters  1902   a ,  1902   b . It should be appreciated that in alternative embodiments, the system  1900  may include any number of filters, and the number of filters and the type of filters may be selected for a certain purpose e.g., for gathering imaging information of a particular body tissue, body condition, chemical process, and so forth. The filters  1902   a ,  1902   b  are configured for preventing unwanted wavelengths of light or other electromagnetic radiation from being sensed by the image sensor  1904 . The filters  1902   a ,  1902   b  may be configured to filter out unwanted wavelengths from white light or other electromagnetic radiation that may be emitted by the light source  1908 . 
     Further to the disclosure with respect to  FIG. 18 , the filters  1902   a ,  1902   b  may be used in an implementation where a fluorescent reagent or dye has been administered. The filters  1902   a ,  1902   b  may be configured for blocking an emitted excitation wavelength for the reagent or dye and permitting the image sensor  1904  to only read the relaxation wavelength of the reagent or dye. Further, the filters  1902   a ,  1902   b  may be used in an implementation where a fluorescent reagent or dye has not been administered. In such an implementation, the filters  1902   a ,  1902   b  may be selected to permit wavelengths corresponding to a desired spectral response to pass through and be read by the image sensor  1904 . 
     The multiple filters  1902   a ,  1902   b  may each be configured for filtering out a different range of wavelengths of the electromagnetic spectrum. For example, one filter may be configured for filtering out wavelengths longer than a desired wavelength range and the additional filter may be configured for filtering out wavelengths shorter than the desired wavelength range. The combination of the two or more filters may result in only a certain wavelength or band of wavelengths being read by the image sensor  1904 . 
     In an embodiment, the filters  1902   a ,  1902   b  are customized such that electromagnetic radiation between 513 nm and 545 nm contacts the image sensor  1904 . In an embodiment, the filters  1902   a ,  1902   b  are customized such that electromagnetic radiation between 565 nm and 585 nm contacts the image sensor  1904 . In an embodiment, the filters  1902   a ,  1902   b  are customized such that electromagnetic radiation between 900 nm and 1000 nm contacts the image sensor  1904 . In an embodiment, the filters  1902   a ,  1902   b  are customized such that electromagnetic radiation between 425 nm and 475 nm contacts the image sensor  1904 . In an embodiment, the filters  1902   a ,  1902   b  are customized such that electromagnetic radiation between 520 nm and 545 nm contacts the image sensor  1904 . In an embodiment, the filters  1902   a ,  1902   b  are customized such that electromagnetic radiation between 625 nm and 645 nm contacts the image sensor  1904 . In an embodiment, the filters  1902   a ,  1902   b  are customized such that electromagnetic radiation between 760 nm and 795 nm contacts the image sensor  1904 . In an embodiment, the filters  1902   a ,  1902   b  are customized such that electromagnetic radiation between 795 nm and 815 nm contacts the image sensor  1904 . In an embodiment, the filters  1902   a ,  1902   b  are customized such that electromagnetic radiation between 370 nm and 420 nm contacts the image sensor  1904 . In an embodiment, the filters  1902   a ,  1902   b  are customized such that electromagnetic radiation between 600 nm and 670 nm contacts the image sensor  1904 . In an embodiment, the filters  1902   a ,  1902   b  are configured for permitting only a certain fluorescence relaxation emission to pass through the filters  1902   a ,  1902   b  and contact the image sensor  1904 . 
     In an embodiment, the system  1900  includes multiple image sensors  1904  and may particularly include two image sensors for use in generating a three-dimensional image. The image sensor(s)  1904  may be color/wavelength agnostic and configured for reading any wavelength of electromagnetic radiation that is reflected off the surface  1912 . In an embodiment, the image sensors  1904  are each color dependent or wavelength dependent and configured for reading electromagnetic radiation of a particular wavelength that is reflected off the surface  1912  and back to the image sensors  1904 . Alternatively, the image sensor  1904  may include a single image sensor with a plurality of different pixel sensors configured for reading different wavelengths or colors of light, such as a Bayer filter color filter array. Alternatively, the image sensor  1904  may include one or more color agnostic image sensors that may be configured for reading different wavelengths of electromagnetic radiation according to a pulsing schedule such as those illustrated in  FIGS. 5-7E , for example. 
       FIG. 20  is a schematic diagram illustrating a system  2000  for mapping a surface and/or tracking an object in a light deficient environment through laser mapping imaging. In an embodiment, an endoscope  2002  in a light deficient environment pulses a grid array  2006  (may be referred to as a laser map pattern) on a surface  2004 . The grid array  2006  includes vertical hashing  2408  and horizontal hashing  2410  in one embodiment as illustrated in  FIG. 20 . It should be appreciated the grid array  2006  may include any suitable array for mapping a surface  2004 , including, for example, a raster grid of discrete points, an occupancy grid map, a dot array, and so forth. Additionally, the endoscope  2002  may pulse multiple grid arrays  2006  and may, for example, pulse one or more individual grid arrays on each of a plurality of objects or structures within the light deficient environment. 
     In an embodiment, the system  2000  pulses a grid array  2006  that may be used for mapping a three-dimensional topology of a surface and/or tracking a location of an object such as a tool or another device in a light deficient environment. In an embodiment, the system  2000  provides data to a third-party system or computer algorithm for determining surface dimensions and configurations by way of light detection and ranging (LIDAR) mapping. The system  2000  may pulse any suitable wavelength of light or electromagnetic radiation in the grid array  2006 , including, for example, ultraviolet light, visible, light, and/or infrared or near infrared light. The surface  2004  and/or objects within the environment may be mapped and tracked at very high resolution and with very high accuracy and precision. 
     In an embodiment, the system  2000  includes an imaging device having a tube, one or more image sensors, and a lens assembly having an optical element corresponding to the one or more image sensors. The system  2000  may include a light engine having an emitter generating one or more pulses of electromagnetic radiation and a lumen transmitting the one or more pulses of electromagnetic radiation to a distal tip of an endoscope within a light deficient environment such as a body cavity. In an embodiment, at least a portion of the one or more pulses of electromagnetic radiation includes a laser map pattern that is emitted onto a surface within the light deficient environment, such as a surface of body tissue and/or a surface of tools or other devices within the body cavity. The endoscope  2002  may include a two-dimensional, three-dimensional, or n-dimensional camera for mapping and/or tracking the surface, dimensions, and configurations within the light deficient environment. 
     In an embodiment, the system  2000  includes a processor for determining a distance of an endoscope or tool from an object such as the surface  2004 . The processor may further determine an angle between the endoscope or tool and the object. The processor may further determine surface area information about the object, including for example, the size of surgical tools, the size of structures, the size of anatomical structures, location information, and other positional data and metrics. The system  2000  may include one or more image sensors that provide image data that is output to a control system for determining a distance of an endoscope or tool to an object such as the surface  2004 . The image sensors may output information to a control system for determining an angle between the endoscope or tool to the object. Additionally, the image sensors may output information to a control system for determining surface area information about the object, the size of surgical tools, size of structures, size of anatomical structures, location information, and other positional data and metrics. 
     In an embodiment, the grid array  2006  is pulsed by an emitter of the endoscope  2002  at a sufficient speed such that the grid array  2006  is not visible to a user. In various implementations, it may be distracting to a user to see the grid array  2006  during an endoscopic imaging procedure and/or endoscopic surgical procedure. The grid array  2006  may be pulsed for sufficiently brief periods such that the grid array  2006  cannot be detected by a human eye. In an alternative embodiment, the endoscope  2002  pulses the grid array  2006  at a sufficient recurring frequency such that the grid array  2006  may be viewed by a user. In such an embodiment, the grid array  2006  may be overlaid on an image of the surface  2004  on a display. The grid array  2006  may be overlaid on a black-and-white or RGB image of the surface  2004  such that the grid array  2006  may be visible by a user during use of the system  2000 . A user of the system  2000  may indicate whether the grid array  2006  should be overlaid on an image of the surface  2004  and/or whether the grid array  2006  should be visible to the user. The system  2000  may include a display that provides real-time measurements of a distance from the endoscope  2002  to the surface  2004  or another object within the light deficient environment. The display may further provide real-time surface area information about the surface  2004  and/or any objects, structures, or tools within the light deficient environment. The accuracy of the measurements may be accurate to less than one millimeter. 
     In an embodiment, the system  2000  pulses a plurality of grid arrays  2006 . In an embodiment, each of the plurality of grid arrays  2006  corresponds to a tool or other device present within the light deficient environment. The precise locations and parameters of each of the tools and other devices may be tracked by pulsing and sensing the plurality of grid arrays  2006 . The information generated by sensing the reflected grid arrays  2006  can be assessed to identify relative locations of the tools and other devices within the light deficient environment. 
     The endoscope  2002  may pulse electromagnetic radiation according to a pulsing schedule such as those illustrated herein that may further include pulsing of the grid array  2006  along with pulsing Red, Green, and Blue light for generating an RGB image and further generating a grid array  2006  that may be overlaid on the RGB image and/or used for mapping and tracking the surface  2004  and objects within the light deficient environment. The grid array  2006  may additionally be pulsed in conjunction with hyperspectral or fluorescent excitation wavelengths of electromagnetic radiation. The data from each of the RGB imaging, the laser mapping imaging, the hyperspectral imaging, and the fluorescence imaging may be combined to identify the locations, dimensions, and surface topology of critical structures in a body. 
     In an embodiment, the endoscope  2002  includes one or more color agnostic image sensors. In an embodiment, the endoscope  2002  includes two color agnostic image sensors for generating a three-dimensional image or map of the light deficient environment. The image sensors may generate an RGB image of the light deficient environment according to a pulsing schedule as disclosed herein. Additionally, the image sensors may determine data for mapping the light deficient environment and tracking one or more objects within the light deficient environment based on data determined when the grid array  2006  is pulsed. Additionally, the image sensors may determine spectral or hyperspectral data along with fluorescence imaging data according to a pulsing schedule that may be modified by a user to suit the particular needs of an imaging procedure. In an embodiment, a pulsing schedule includes Red, Green, and Blue pulses along with pulsing of a grid array  2006  and/or pulsing for generating hyperspectral image data and/or fluorescence image data. In various implementations, the pulsing schedule may include any suitable combination of pulses of electromagnetic radiation according to the needs of a user. The recurring frequency of the different wavelengths of electromagnetic radiation may be determined based on, for example, the energy of a certain pulse, the needs of the user, whether certain data (for example, hyperspectral data and/or fluorescence imaging data) needs to be continuously updated or may be updated less frequently, and so forth. 
     The pulsing schedule may be modified in any suitable manner, and certain pulses of electromagnetic radiation may be repeated at any suitable frequency, according to the needs of a user or computer-implemented program for a certain imaging procedure. For example, in an embodiment where surface tracking data generated based on the grid array  2006  is provided to a computer-implemented program for use in, for example, a robotic surgical procedure, the grid array  2006  may be pulsed more frequently than if the surface tracking data is provided to a user who is visualizing the scene during the imaging procedure. In such an embodiment where the surface tracking data is used for a robotic surgical procedure, the surface tracking data may need to be updated more frequently or may need to be exceedingly accurate such that the computer-implemented program may execute the robotic surgical procedure with precision and accuracy. 
     In an embodiment, the system  2000  is configured to generate an occupancy grid map comprising an array of cells divided into grids. The system  2000  is configured to store height values for each of the respective grid cells to determine a surface mapping of a three-dimensional environment in a light deficient environment. 
       FIGS. 21A and 21B  illustrate a perspective view and a side view, respectively, of an implementation of an imaging sensor  1900  built on a plurality of substrates. As illustrated, a plurality of pixel columns  1904  forming the pixel array are located on the first substrate  1902  and a plurality of circuit columns  1908  are located on a second substrate  1906 . Also illustrated in the figure are the electrical connection and communication between one column of pixels to its associated or corresponding column of circuitry. In one implementation, an image sensor, which might otherwise be manufactured with its pixel array and supporting circuitry on a single, monolithic substrate/chip, may have the pixel array separated from all or a majority of the supporting circuitry. The disclosure may use at least two substrates/chips, which will be stacked together using three-dimensional stacking technology. The first  1902  of the two substrates/chips may be processed using an image CMOS process. The first substrate/chip  1902  may be comprised either of a pixel array exclusively or a pixel array surrounded by limited circuitry. The second or subsequent substrate/chip  1906  may be processed using any process and does not have to be from an image CMOS process. The second substrate/chip  1906  may be, but is not limited to, a highly dense digital process to integrate a variety and number of functions in a very limited space or area on the substrate/chip, or a mixed-mode or analog process to integrate for example precise analog functions, or a RF process to implement wireless capability, or MEMS (Micro-Electro-Mechanical Systems) to integrate MEMS devices. The image CMOS substrate/chip  1902  may be stacked with the second or subsequent substrate/chip  1906  using any three-dimensional technique. The second substrate/chip  1906  may support most, or a majority, of the circuitry that would have otherwise been implemented in the first image CMOS chip  1902  (if implemented on a monolithic substrate/chip) as peripheral circuits and therefore have increased the overall system area while keeping the pixel array size constant and optimized to the fullest extent possible. The electrical connection between the two substrates/chips may be done through interconnects, which may be wire bonds, bump and/or TSV (Through Silicon Via). 
       FIGS. 22A and 22B  illustrate a perspective view and a side view, respectively, of an implementation of an imaging sensor  2200  having a plurality of pixel arrays for producing a three-dimensional image. The three-dimensional image sensor may be built on a plurality of substrates and may comprise the plurality of pixel arrays and other associated circuitry, wherein a plurality of pixel columns  2204   a  forming the first pixel array and a plurality of pixel columns  2204   b  forming a second pixel array are located on respective substrates  2202   a  and  2202   b , respectively, and a plurality of circuit columns  2208   a  and  2208   b  are located on a separate substrate  2206 . Also illustrated are the electrical connections and communications between columns of pixels to associated or corresponding column of circuitry. 
       FIGS. 23A and 23B  illustrate a perspective view and a side view, respectively, of an implementation of a monolithic sensor  2300  having a plurality of pixel arrays for producing a three-dimensional image in accordance with the teachings and principles of the disclosure. Such an implementation may be desirable for three-dimensional image capture, wherein the two-pixel arrays  2302  and  2304  may be offset during use. In another implementation, a first pixel array  2302  and a second pixel array  2304  may be dedicated to receiving a predetermined range of wave lengths of electromagnetic radiation, wherein the first pixel array is dedicated to a different range of wavelength electromagnetic radiation than the second pixel array. 
     The plurality of pixel arrays may sense information simultaneously and the information from the plurality of pixel arrays may be combined to generate a three-dimensional image. In an embodiment, an endoscopic imaging system includes two or more pixel arrays that can be deployed to generate three-dimensional imaging. The endoscopic imaging system may include an emitter for emitting pulses of electromagnetic radiation during a blanking period of the pixel arrays. The pixel arrays may be synced such that the optical black pixels are read (i.e., the blanking period occurs) at the same time for the two or more pixel arrays. The emitter may emit pulses of electromagnetic radiation for charging each of the two or more pixel arrays. The two or more pixel arrays may read their respective charged pixels at the same time such that the readout periods for the two or more pixel arrays occur at the same time or at approximately the same time. In an embodiment, the endoscopic imaging system includes multiple emitters that are each individual synced with one or more pixel arrays of a plurality of pixel arrays. Information from a plurality of pixel arrays may be combined to generate three-dimensional image frames and video streams. 
     It will be appreciated that the teachings and principles of the disclosure may be used in a reusable device platform, a limited use device platform, a re-posable use device platform, or a single use/disposable device platform without departing from the scope of the disclosure. It will be appreciated that in a re-usable device platform an end-user is responsible for cleaning and sterilization of the device. In a limited use device platform, the device can be used for some specified amount of times before becoming inoperable. Typical new device is delivered sterile with additional uses requiring the end-user to clean and sterilize before additional uses. In a re-posable use device platform, a third-party may reprocess the device (e.g., cleans, packages and sterilizes) a single-use device for additional uses at a lower cost than a new unit. In a single use/disposable device platform a device is provided sterile to the operating room and used only once before being disposed of. 
     EXAMPLES 
     The following examples pertain to preferred features of further embodiments: 
     Example 1 is a method. The method includes actuating an emitter to emit a plurality of pulses of electromagnetic radiation. The method includes sensing reflected electromagnetic radiation resulting from the plurality of pulses of electromagnetic radiation with a pixel array of an image sensor to generate a plurality of exposure frames. The method includes detecting motion across two or more sequential exposure frames of the plurality of exposure frames. The method includes compensating for the detected motion. The method includes combining the two or more sequential exposure frames to generate an image frame. The method is such that at least a portion of the plurality of pulses of electromagnetic radiation emitted by the emitter comprises a laser mapping pattern. 
     Example 2 is a method as in Example 1, wherein compensating for the detected motion comprises: upscaling a first exposure frame of the two or more sequential exposure frames using interpolation to generate a first upscaled frame; upscaling the first exposure frame without using interpolation to generate a second upscaled frame, wherein the second upscaled frame comprises a first set of empty pixels; and filling in the first set of empty pixels of the second upscaled frame with pixel data from the first upscaled frame. 
     Example 3 is a method as in any of Examples 1-2, wherein compensating for the detected motion further comprises: upscaling a second exposure frame of the two or more sequential exposure frames to generate a third upscaled frame; and filling in a second set of empty pixels in the second upscaled frame with pixel data from the third upscaled frame. 
     Example 4 is a method as in any of Examples 1-3, wherein the two or more sequential exposure frames comprises a red exposure frame, a green exposure frame, and a blue exposure frame, and wherein combining the two or more sequential exposure frames to generate the image frame comprises generating a Red Green Blue (“RGB”) image frame. 
     Example 5 is a method as in any of Examples 1-4, wherein the two or more sequential exposure frames comprises a luminance (Y) exposure frame, a chrominance blue (Cb) exposure frame, and a chrominance red (Cr) exposure frame, and wherein combining the two or more sequential exposure frames to generate the image frame comprises generating a YCbCr image frame. 
     Example 6 is a method as in any of Examples 1-5, wherein sensing the reflected electromagnetic radiation comprises: generating a first exposure frame based on a pulse of electromagnetic radiation of a first color partition; generating a second exposure frame based on a pulse of electromagnetic radiation of a second color partition; and generating a third exposure frame based on a pulse of electromagnetic radiation of the first color partition; wherein the second exposure frame is captured between the first exposure frame and the third exposure frame; wherein detecting motion across the two or more sequential exposure frames comprises calculating a relative motion estimate based on the first exposure frame and the third exposure frame using block matching; and wherein compensating for the detected motion comprises generating a motion compensated frame for the second exposure frame based on the relative motion estimate. 
     Example 7 is a method as in any of Examples 1-6, further comprising: determining a first motion vector for the first exposure frame and a second motion vector for the second exposure frame; and shifting a block of pixels in the first exposure frame by the first motion vector. 
     Example 8 is a method as in any of Examples 1-7, further comprising: performing bilinear interpolation on luminance data in the two or more sequential exposure frames to generate a first upscaled dataset; performing bicubic interpolation on the luminance data to generate a second upscaled dataset; and calculating a baseline with no interpolation of the luminance data to generate a third upscaled dataset. 
     Example 9 is a method as in any of Examples 1-8, wherein detecting motion across two or more sequential exposure frames comprises one or more of: segmenting data sensed by the pixel array into segments of pixels and nearest neighboring exposure frames; shifting each segment of pixels in the x direction and comparing with a neighboring exposure frame at a same resolution to identify motion of an object being imaged in the x direction; shifting each segment of pixels in the x direction in sub-pixel increments and comparing to the first upscaled dataset to identify motion of the object being imaged in the x direction with increased precision; shifting each segment of pixels in the y direction and comparing with a neighboring exposure frame to identify motion of an object being imaged in the y direction; or shifting each segment of pixels in the y direction in sub-pixel increments and comparing to the first upscaled dataset to identify motion of the object being imaged in the y direction with increased precision. 
     Example 10 is a method as in any of Examples 1-9, wherein sensing the reflected electromagnetic radiation comprises sensing during a readout period of the pixel array, wherein the readout period is a duration of time when active pixels in the pixel array are read. 
     Example 11 is a method as in any of Examples 1-10, wherein actuating the emitter comprises actuating the emitter to emit, during a pulse duration, a plurality of sub-pulses of electromagnetic radiation having a sub-duration shorter than the pulse duration. 
     Example 12 is a method as in any of Examples 1-11, wherein actuating the emitter comprises actuating the emitter to emit two or more wavelengths simultaneously as a single pulse or a single sub-pulse. 
     Example 13 is a method as in any of Examples 1-12, wherein actuating the emitter comprises actuating the emitter to pulse the laser mapping pattern at a duration and frequency such that the laser mapping pattern is not visible to a user of the system. 
     Example 14 is a method as in any of Examples 1-13, wherein sensing the reflected electromagnetic radiation comprises generating a fluorescence exposure frame, and wherein the method further comprises providing the fluorescence exposure frame to a corresponding fluorescence system that determines a location of a critical tissue structure within a scene based on the fluorescence exposure frame. 
     Example 15 is a method as in any of Examples 1-14, further comprising: receiving the location of the critical tissue structure from the corresponding fluorescence system; generating an overlay frame comprising the location of the critical tissue structure; and combining the overlay frame with a color image frame depicting the scene to indicate the location of the critical tissue structure within the scene. 
     Example 16 is a method as in any of Examples 1-15, wherein sensing reflected electromagnetic by the pixel array comprises sensing reflected electromagnetic radiation resulting from the laser mapping pattern to generate a laser mapping exposure frame, and wherein the method further comprises: providing the laser mapping exposure frame to a corresponding laser mapping system that determines a topology of the scene and/or dimensions of one or more objects within the scene; provide the location of the critical tissue structure to the corresponding laser mapping system; and receive a topology and/or dimension of the critical tissue structure from the corresponding laser mapping system. 
     Example 17 is a method as in any of Examples 1-16, wherein the critical tissue structure comprises one or more of a nerve, a ureter, a blood vessel, an artery, a blood flow, or a tumor. 
     Example 18 is a method as in any of Examples 1-17, further comprising synchronizing timing of the plurality of pulses of electromagnetic radiation to be emitted during a blanking period of the image sensor, wherein the blanking period corresponds to a time between a readout of a last row of active pixels in the pixel array and a beginning of a next subsequent readout of active pixels in the pixel array. 
     Example 19 is a method as in any of Examples 1-18, wherein the two or more sequential exposure frames are captured sequentially in time based on two or more pulses of electromagnetic radiation emitted by the emitter sequentially in time. 
     Example 20 is a method as in any of Examples 1-19, wherein sensing the reflected electromagnetic radiation comprises sensing with a first pixel array and a second pixel array such that a three-dimensional image can be generated based on the sensed reflected electromagnetic radiation. 
     Example 21 is a method as in any of Examples 1-20, wherein actuating the emitter comprises actuating the emitter to emit a sequence of pulses of electromagnetic radiation repeatedly sufficient for generating a video stream comprising a plurality of image frames, wherein each image frame in the video stream comprises data from a plurality of exposure frames, and wherein each of the exposure frames corresponds to a pulse of electromagnetic radiation. 
     Example 22 is a method as in any of Examples 1-21, wherein sensing reflected electromagnetic radiation by the pixel array comprises generating a laser mapping exposure frame by sensing reflected electromagnetic radiation resulting from the emitter pulsing the laser mapping pattern, wherein the laser mapping exposure frame comprises information for determining real time measurements comprising one or more of: a distance from an endoscope to an object; an angle between an endoscope and the object; or surface topology information about the object. 
     Example 23 is a method as in any of Examples 1-22, wherein the laser mapping exposure frame comprises information for determining the real time measurements to an accuracy of less than 10 centimeters. 
     Example 24 is a method as in any of Examples 1-23, wherein the laser mapping exposure frame comprises information for determining the real time measurements to an accuracy of less than one millimeter. 
     Example 25 is a method as in any of Examples 1-24, wherein actuating the emitter to emit the plurality of pulses of electromagnetic radiation comprises actuating the emitter to emit a plurality of tool-specific laser mapping patterns for each of a plurality of tools within a scene. 
     Example 26 is a method as in any of Examples 1-25, wherein the laser mapping pattern emitted by the emitter comprises a first output and a second output that are independent from one another, wherein the first output is for light illumination and the second output is for tool tracking. 
     Example 27 is means for performing any of the method steps recited in Examples 1-26. 
     It will be appreciated that various features disclosed herein provide significant advantages and advancements in the art. The following claims are exemplary of some of those features. 
     In the foregoing Detailed Description of the Disclosure, various features of the disclosure are grouped together in a single embodiment for the purpose of streamlining the disclosure. This method of disclosure is not to be interpreted as reflecting an intention that the claimed disclosure requires more features than are expressly recited in each claim. Rather, inventive aspects lie in less than all features of a single foregoing disclosed embodiment. 
     It is to be understood that any features of the above-described arrangements, examples, and embodiments may be combined in a single embodiment comprising a combination of features taken from any of the disclosed arrangements, examples, and embodiments. 
     It is to be understood that the above-described arrangements are only illustrative of the application of the principles of the disclosure. Numerous modifications and alternative arrangements may be devised by those skilled in the art without departing from the spirit and scope of the disclosure and the appended claims are intended to cover such modifications and arrangements. 
     Thus, while the disclosure has been shown in the drawings and described above with particularity and detail, it will be apparent to those of ordinary skill in the art that numerous modifications, including, but not limited to, variations in size, materials, shape, form, function and manner of operation, assembly and use may be made without departing from the principles and concepts set forth herein. 
     The foregoing description has been presented for the purposes of illustration and description. It is not intended to be exhaustive or to limit the disclosure to the precise form disclosed. Many modifications and variations are possible in light of the above teaching. Further, it should be noted that any or all the aforementioned alternate implementations may be used in any combination desired to form additional hybrid implementations of the disclosure. 
     Further, although specific implementations of the disclosure have been described and illustrated, the disclosure is not to be limited to the specific forms or arrangements of parts so described and illustrated. The scope of the disclosure is to be defined by the claims appended hereto, any future claims submitted here and in different applications, and their equivalents.