Abstract:
A system and a method for acquiring image data of a subject with an imaging system is provided. The system can include a gantry that completely annularly encompasses at least a portion of the subject, with a source positioned within and movable relative to the gantry. The source can be responsive to a signal to output at least one pulse. The system can include a detector positioned within and movable relative to the gantry to detect the pulse emitted by the source. The system can also include a detector control module that sets detector data based on the detected pulse, and an image acquisition control module that sets the signal for the source and receives the detector data. The image acquisition control module can reconstruct image data based on the detector data. The signal can include a signal for the source to output a single pulse or two pulses.

Description:
CROSS-REFERENCE TO RELATED APPLICATIONS 
       [0001]    This application is a continuation application of U.S. patent application Ser. No. 13/014,886 filed on Jan. 27, 2011, the entire disclosure of which is incorporated by reference herein. 
     
    
     FIELD 
       [0002]    The present disclosure relates to imaging a subject, and particularly to an optimal image acquisition procedure for an imaging device. 
       BACKGROUND 
       [0003]    This section provides background information related to the present disclosure which is not necessarily prior art. 
         [0004]    A subject, such as a human patient, may select or be required to undergo a surgical procedure to correct or augment an anatomy of the patient. The augmentation of the anatomy can include various procedures, such as movement or augmentation of bone, insertion of implantable devices, or other appropriate procedures. A surgeon can perform the procedure on the subject with images of the patient that can be acquired using imaging systems such as a magnetic resonance imaging (MRI) system, computed tomography (CT) system, fluoroscopy (e.g., C-Arm imaging systems), or other appropriate imaging systems. 
         [0005]    Images of a patient can assist a surgeon in performing a procedure including planning the procedure and performing the procedure. A surgeon may select a two dimensional image or a three dimensional image representation of the patient. The images can assist the surgeon in performing a procedure with a less invasive technique by allowing the surgeon to view the anatomy of the patient without removing the overlying tissue (including dermal and muscular tissue) when performing a procedure. 
       SUMMARY 
       [0006]    This section provides a general summary of the disclosure, and is not a comprehensive disclosure of its full scope or all of its features. 
         [0007]    According to various embodiments, provided is a system for acquiring image data of a subject with an imaging system. The system can include a gantry that completely annularly encompasses at least a portion of the subject. The system can also include a source positioned within and movable relative to the gantry. The source can be responsive to a signal to output at least one pulse. The system can include a detector positioned within and movable relative to the gantry and the source to detect the at least one pulse emitted by the source. The system can also include a detector control module that sets detector data based on the detected at least one pulse, and an image acquisition control module that sets the signal for the source and receives the detector data. The image acquisition control module can be operable to reconstruct image data based on the detector data. The signal can include a signal for the source to output a single pulse or a signal for the source to output two pulses. 
         [0008]    Further provided is a method for acquiring image data of a subject with an imaging system. The method can include positioning a gantry to completely annularly encompass at least a portion of the subject, with a source and a detector positioned within and movable relative to the gantry. The method can also include receiving at least one user input that provides a request for an output for the source, and determining, based on the user input, a type of output for the source. The method can include outputting one pulse with the source or substantially simultaneously outputting two pulses with the source, and receiving the one pulse or two pulses with the detector. The method can also include reconstructing, based on the one pulse or two pulses received by the detector, an image of the subject. 
         [0009]    Also provided is a method for acquiring image data of a subject with an imaging system. The method can include positioning a gantry to completely annularly encompass at least a portion of the subject, with a source and a detector positioned within and movable relative to the gantry. The method can include outputting a first pulse having a first pulse rate with the source, and substantially simultaneously outputting a second pulse with a second pulse rate with the source, the second pulse rate being different than the first pulse rate. The method can include receiving the first pulse and the second pulse with the detector, and reconstructing, based on first pulse and the second pulse received by the detector, an image of the subject. 
         [0010]    Further areas of applicability will become apparent from the description provided herein. The description and specific examples in this summary are intended for purposes of illustration only and are not intended to limit the scope of the present disclosure. 
     
    
     
       DRAWINGS 
         [0011]    The drawings described herein are for illustrative purposes only of selected embodiments and not all possible implementations, and are not intended to limit the scope of the present disclosure. 
           [0012]      FIG. 1  is an environmental view of an exemplary imaging system in an operating theatre; 
           [0013]      FIG. 2  is a schematic illustration of an exemplary computing system for use with the imaging system of  FIG. 1 ; 
           [0014]      FIG. 3  is a simplified block diagram illustrating a system for implementing an image acquisition control module according to various embodiments; 
           [0015]      FIG. 4  is a dataflow diagram illustrating an exemplary control system performed by the image acquisition control module of  FIG. 3 ; 
           [0016]      FIG. 5  is a flowchart illustrating a method performed by the image acquisition control module; 
           [0017]      FIG. 6  is a continuation of the flowchart of  FIG. 5  at A; 
           [0018]      FIG. 7  is a continuation of the flowchart of  FIG. 5  at B; 
           [0019]      FIG. 8  is a continuation of the flowchart of  FIG. 5  at C; and 
           [0020]      FIG. 9  is a schematic timing diagram for a dual energy output for the imaging system of  FIG. 1 . 
       
    
    
     DETAILED DESCRIPTION 
       [0021]    The following description is merely exemplary in nature. It should be understood that throughout the drawings, corresponding reference numerals indicate like or corresponding parts and features. As indicated above, the present teachings are directed toward providing optimized image acquisition for an imaging device, such as an O-Arm® imaging system sold by Medtronic Navigation, Inc. having a place of business in Louisville, Colo., USA. It should be noted, however, that the present teachings could be applicable to any appropriate imaging device, such as a C-arm imaging device. Further, as used herein, the term “module” can refer to a computer readable media that can be accessed by a computing device, an application specific integrated circuit (ASIC), an electronic circuit, a processor (shared, dedicated, or group) and memory that executes one or more software or firmware programs, a combinational logic circuit, and/or other suitable software, firmware programs or components that provide the described functionality. In addition, it should be noted that the values provided herein for the pulse rate in kilovolts and width in milliseconds are merely exemplary as both the pulse rate and width can vary based upon the particular patient and clinical scenario, such as in the case of a pediatric patient. 
         [0022]    With reference to  FIG. 1 , in an operating theatre or operating room  10 , a user, such as a user  12 , can perform a procedure on a patient  14 . In performing the procedure, the user  12  can use an imaging system  16  to acquire image data of the patient  14  for performing a procedure. The image data acquired of the patient  14  can include two-dimension (2D) projections acquired with an x-ray imaging system, including those disclosed herein. It will be understood, however, that 2D forward projections of a volumetric model can also be generated, also as disclosed herein. 
         [0023]    In one example, a model can be generated using the acquired image data. The model can be a three-dimension (3D) volumetric model generated based on the acquired image data using various techniques, including algebraic iterative techniques, also as discussed further herein. Displayed image data  18  can be displayed on a display device  20 , and additionally, could be displayed on a display device  32   a  associated with an imaging computing system  32 , as will be discussed in greater detail herein. The displayed image data  18  can be a 2D image, a 3D image, or a time changing four-dimension image. The displayed image data  18  can also include the acquired image data, the generated image data, both, or a merging of both the types of image data. 
         [0024]    It will be understood that the image data acquired of the patient  14  can be acquired as 2D projections, for example with an x-ray imaging system. The 2D projections can then be used to reconstruct the 3D volumetric image data of the patient  14 . Also, theoretical or forward 2D projections can be generated from the 3D volumetric image data. Accordingly, it will be understood that image data can be either or both of 2D projections or 3D volumetric models. 
         [0025]    The display device  20  can be part of a computing system  22 . The computing system  22  can include a variety of computer-readable media. The computer-readable media can be any available media that can be accessed by the computing system  22  and can include both volatile and non-volatile media, and removable and non-removable media. By way of example, and not limitation, the computer-readable media can comprise computer storage media and communication media. Storage media includes, but is not limited to, RAM, ROM, EEPROM, flash memory or other memory technology, CD-ROM, Digital Versatile Disk (DVD) or other optical disk storage, magnetic cassettes, magnetic tape, magnetic disk storage or other magnetic storage devices, or any other medium which can be used to store computer-readable instructions, software, data structures, program modules, and other data and which can be accessed by the computing system  22 . The computer-readable media may be accessed directly or through a network such as the Internet. 
         [0026]    In one example, the computing system  22  can include an input device  24 , such as a keyboard, and one or more processors  26  (the one or more processors can include multiple-processing core processors, microprocessors, etc.) that can be incorporated with the computing system  22 . The input device  24  can comprise any suitable device to enable a user to interface with the computing system  22 , such as a touchpad, touch pen, touch screen, keyboard, mouse, joystick, trackball, wireless mouse, or a combination thereof. Furthermore, while the computing system  22  is described and illustrated herein as comprising the input device  24  discrete from the display device  20 , the computing system  22  could comprise a touchpad or tablet computing device, and further, that the computing system  22  could be integrated within or be part of the imaging computing system  32  associated with the imaging system  16 . 
         [0027]    A connection  28  can be provided between the computing system  22  and the display device  20  for data communication to allow driving the display device  20  to illustrate the image data  18 . 
         [0028]    The imaging system  16  can include the O-Arm® imaging system sold by Medtronic Navigation, Inc. having a place of business in Louisville, Colo., USA. The imaging system  16 , including the O-Arm® imaging system, or other appropriate imaging systems in use during a selected procedure are also described in U.S. patent application Ser. No. 12/465,206, entitled “System And Method For Automatic Registration Between An Image And A Subject,” filed on May 13, 2009, incorporated herein by reference. Additional description regarding the O-Arm imaging system or other appropriate imaging systems can be found in U.S. Pat. Nos. 7,188,998, 7,108,421, 7,106,825, 7,001,045 and 6,940,941, each of which is incorporated herein by reference. 
         [0029]    The O-Arm® imaging system  16  can include a mobile cart  30  that includes the imaging computing system  32  and an imaging gantry  34  in which is positioned a source unit  36  and a detector  38 . With reference to  FIG. 2 , a diagram is provided that illustrates an exemplary embodiment of the imaging computing system  32 , some or all of the components of which can be used in conjunction with the teachings of the present disclosure. The imaging computing system  32  can include a variety of computer-readable media. The computer-readable media can be any available media that can be accessed by the imaging computing system  32  and includes both volatile and non-volatile media, and removable and non-removable media. By way of example, and not limitation, the computer-readable media can comprise computer storage media and communication media. Storage media includes, but is not limited to, RAM, ROM, EEPROM, flash memory or other memory technology, CD-ROM, Digital Versatile Disk (DVD) or other optical disk storage, magnetic cassettes, magnetic tape, magnetic disk storage or other magnetic storage devices, or any other medium which can be used to store computer-readable instructions, software, data structures, program modules, and other data and which can be accessed by the imaging computing system  32 . The computer-readable media may be accessed directly or through a network such as the Internet. 
         [0030]    In one example, the imaging computing system  32  comprises a display device  32   a  and a system unit  32   b . As illustrated, the display device  32   a  can comprise a computer video screen or monitor. The imaging computing system  32  can also include at least one input device  32   c . The system unit  32   b  includes, as shown in an exploded view at  100 , a processor  102  and a memory  104 , which can include software  106  and data  108 . 
         [0031]    In this example, the at least one input device  32   c  comprises a keyboard. It should be understood, however, that the at least one user input device  32   c  can comprise any suitable device to enable a user to interface with the imaging computing system  32 , such as a touchpad, touch pen, touch screen, keyboard, mouse, joystick, trackball, wireless mouse, or a combination thereof. Furthermore, while the imaging computing system  32  is described and illustrated herein as comprising the system unit  32   b  with the display device  32   a , the imaging computing system  32  could comprise a touchpad or tablet computing device. 
         [0032]    As will be discussed with regard to  FIGS. 3-9 , the imaging computing system  32  can control the source  36  and the detector  38  to optimize image data acquisition via an image acquisition control module  110 , which can be stored in the memory  104  and accessed by the processor  102 . A connection can be provided between the processor  102  and the display device  32   a  for data communication to allow driving the display device  32   a  to illustrate the image data  18 . 
         [0033]    With reference to  FIG. 1 , the mobile cart  30  can be moved from one operating theater or room to another and the gantry  34  can move relative to the mobile cart  30 , as discussed further herein. This allows the imaging system  16  to be mobile allowing it to be used in multiple locations and with multiple procedures without requiring a capital expenditure or space dedicated to a fixed imaging system. 
         [0034]    The source unit  36  can emit x-rays through the patient  14  to be detected by the detector  38 . As is understood by one skilled in the art, the x-rays emitted by the source  36  can be emitted in a cone and detected by the detector  38 . The source  36 /detector  38  is generally diametrically opposed within the gantry  34 . The detector  38  can move rotationally in a 360° motion around the patient  14  generally in the directions of arrow  39  within the gantry  34  with the source  36  remaining generally 180° from and opposed to the detector  38 . Also, the gantry  34  can isometrically sway or swing (herein also referred to as iso-sway) generally in the direction of arrow  40 , relative to the patient  14 , which can be placed on a patient support or table  15 . The gantry  34  can also tilt relative to the patient  14  illustrated by arrows  42 , move longitudinally along the line  44  relative to the patient  14  and the mobile cart  30 , can move up and down generally along the line  46  relative to the mobile cart  30  and transversely to the patient  14 , and move perpendicularly generally in the direction of arrow  48  relative to the patient  14  to allow for positioning of the source  36 /detector  38  at any desired position relative to the patient  14 . 
         [0035]    The O-Arm® imaging system  16  can be precisely controlled by the imaging computing system  32  to move the source  36 /detector  38  relative to the patient  14  to generate precise image data of the patient  14 . In addition, the imaging system  16  can be connected with the processor  26  via connection  50  which can include a wired or wireless connection or physical media transfer from the imaging system  16  to the processor  26 . Thus, image data collected with the imaging system  16  can also be transferred from the imaging computing system  32  to the computing system  22  for navigation, display, reconstruction, etc. 
         [0036]    Briefly, according to various embodiments, the imaging system  16  can be used with an unnavigated or navigated procedure. In a navigated procedure, a localizer, including either or both of an optical localizer  60  and an electromagnetic localizer  62  can be used to generate a field or receive or send a signal within a navigation domain relative to the patient  14 . The navigated space or navigational domain relative to the patient  14  can be registered to the image data  18  to allow registration of a navigation space defined within the navigational domain and an image space defined by the image data  18 . A patient tracker or a dynamic reference frame  64  can be connected to the patient  14  to allow for a dynamic registration and maintenance of registration of the patient  14  to the image data  18 . 
         [0037]    An instrument  66  can then be tracked relative to the patient  14  to allow for a navigated procedure. The instrument  66  can include an optical tracking device  68  and/or an electromagnetic tracking device  70  to allow for tracking of the instrument  66  with either or both of the optical localizer  60  or the electromagnetic localizer  62 . The instrument  66  can include a communication line  72  with a navigation interface device  74  as can the electromagnetic localizer  62  and/or the optical localizer  60 . Using the communication lines  74 ,  78  respectively, the probe interface  74  can then communicate with the processor  26  with a communication line  80 . It will be understood that any of the connections or communication lines  28 ,  50 ,  76 ,  78 , or  80  can be wired, wireless, physical media transmission or movement, or any other appropriate communication. Nevertheless, the appropriate communication systems can be provided with the respective localizers to allow for tracking of the instrument  66  relative to the patient  14  to allow for illustration of the tracked location of the instrument  66  relative to the image data  18  for performing a procedure. 
         [0038]    It will be understood that the instrument  66  can be an interventional instrument and/or an implant. Implants can include a ventricular or vascular stent, a spinal implant, neurological stent or the like. The instrument  66  can be an interventional instrument such as a deep brain or neurological stimulator, an ablation device, or other appropriate instrument. Tracking the instrument  66  allows for viewing the location of the instrument  66  relative to the patient  14  with use of the registered image data  18  and without direct viewing of the instrument  66  within the patient  14 . 
         [0039]    Further, the imaging system  16  can include a tracking device, such as an optical tracking device  82  or an electromagnetic tracking device  84  to be tracked with a respective optical localizer  60  or the electromagnetic localizer  62 . The tracking device can be associated directly with the source  36 , the detector  38 , the gantry  34 , or other appropriate part of the imaging system  16  to determine the location or position of the detector  38  relative to a selected reference frame. As illustrated, the tracking device  82 ,  84  can be positioned on the exterior of the housing of the gantry  34 . Accordingly, the imaging system  16  can be tracked relative to the patient  14  as can the instrument  66  to allow for initial registration, automatic registration or continued registration of the patient  14  relative to the image data  18 . Registration and navigated procedures are discussed in the above incorporated U.S. patent application Ser. No. 12/465,206. 
         [0040]    Further, with continued reference to  FIG. 1 , the operating theatre  10  can optionally include a gating device or an electrocardiogram or ECG  112 , which is attached to the patient  14 , via skin electrodes, and in communication with the imaging computing system  32 . Respiration and cardiac motion can cause movement of cardiac structures relative to the imaging system  16 . Therefore, images can be acquired from the imaging system  16  based on a time-gated basis triggered by a physiological signal. For example, the ECG or EGM signal may be acquired from the skin electrodes or from a sensing electrode included on the instrument  66  or from a separate reference probe (not shown). A characteristic of this signal, such as an R-wave peak or P-wave peak associated with ventricular or atrial depolarization, respectively, may be used as a triggering event for the imaging computing system  32  to drive the source  36 . By time-gating the acquisition of the image data  18 , the image data  18  can be reconstructed to provide a 3D view of an organ of interest in a particular phase, as will be discussed in greater detail herein. 
         [0041]    It should be noted that in a navigated procedure, the ECG  112  can also be use to time-gate the navigation data. In this regard, the characteristic of the signal, such as the R-wave peak or P-wave peak associated with ventricular or atrial depolarization, respectively, can be used as a triggering event for driving the coils in the electromagnetic localizer  62 . Further detail regarding the time-gating of the navigation data can be found in U.S. Pat. No. 7,599,730, entitled “Navigation System for Cardiac Therapies,” filed Nov. 19, 2002, which is hereby incorporated by reference. 
         [0042]    With reference to  FIG. 3 , a simplified block diagram schematically illustrates an exemplary system  114  for implementing the image acquisition control module  110  according to various embodiments. In one example, the image acquisition control module  110  can be implemented by the imaging computing system  32  of the imaging system  16 . The image acquisition control module  110  can receive user input from the input device  32   c . Note that while the display is illustrated and described herein as comprising the display device  32   a , the imaging computing system  32  could output image data  18  to the display device  20 . 
         [0043]    The image acquisition control module  110  can send a source output signal  116  to the source  36 . As will be discussed, the source output signal  116  can comprise a signal for the source  36  to output or emit at least one or more x-ray pulses  118   a  . . .  118   n  at a particular pulse rate and pulse width. 
         [0044]    The image acquisition control module  110  can also output a move signal  120  to the source  36  to move the position of the source  36  within the gantry  34 , and the image acquisition control module  110  can also output a move signal  122  to the detector  38  to move the position of the detector  38  within the gantry  34 . Generally, the source  36  and the detector  38  can move about 360° around a longitudinal axis  14 L of the patient  14  within the gantry  34 . The movement of the detector  38  and the source  36  relative to the patient  14  can allow the imaging system  16  to acquire image data at a plurality of selected locations and orientations relative to the subject  14 . 
         [0045]    In this regard, the 2D projection image data can be acquired by substantially annular or 360° orientation movement of the source  36 /detector  38  around the patient  14  due to positioning of the source  36 /detector  38  moving around the patient  14  in the optimal movement. Also, due to movements of the gantry  34 , the source  36 /detector  38  need never move in a pure circle, but rather can move in a spiral helix, or other rotary movement about or relative to the patient  14 . Also, the path can be substantially non-symmetrical and/or non-linear based on movements of the imaging system  16 , including the gantry  34  and the source  36 /detector  38  together. In other words, the path need not be continuous in that the source  36 /detector  38  and the gantry  34  can stop, move back from the direction from which it just came (e.g., oscillate), etc. in following the optimal path. Thus, the source  36 /detector  38  need never travel a full 360° around the patient  14  as the gantry  34  may tilt or otherwise move and the source  36 /detector  38  may stop and move back in the direction it has already passed. Further detail regarding the movement of the source  36  and the detector  38  can be found in U.S. Pat. No. 7,108,421, entitled “Systems and Methods for Imaging Large Field-of-View Objects,” filed on Mar. 18, 2003 and incorporated herein by reference. 
         [0046]    With continued reference to  FIG. 3 , the pulses  118   a  . . .  118   n  can be received by the detector  38 . The detector  38  can transmit a signal  120  regarding the received pulses to the image acquisition control module  110 . Based on the signal(s)  120  received from the detector  38 , the image acquisition control module  110  can generate the image data  18  on the display device  32   a  or the display device  20 . 
         [0047]    In this regard, the image acquisition control module  110  can perform automatic reconstruction of an initial three dimensional model of the area of interest of the patient  14 . Reconstruction of the three dimensional model can be performed in any appropriate manner, such as using an algebraic techniques for optimization. Appropriate algebraic techniques include Expectation maximization (EM), Ordered Subsets EM (OS-EM), Simultaneous Algebraic Reconstruction Technique (SART) and total variation minimization, as generally understood by those skilled in the art. The application to performing a 3D volumetric reconstruction based on the 2D projections allows for efficient and complete volumetric reconstruction. 
         [0048]    Generally, an algebraic technique can include an iterative process to perform a reconstruction of the patient  14  for display as the image data  18 . For example, a pure or theoretical image data projection, such as those based on or generated from an atlas or stylized model of a “theoretical” patient, can be iteratively changed until the theoretical projection images match the acquired 2D projection image data of the patient  14 . Then, the stylized model can be appropriately altered as the 3D volumetric reconstruction model of the acquired 2D projection image data of the selected patient  14  and can be used in a surgical intervention, such as navigation, diagnosis, or planning. The theoretical model can be associated with theoretical image data to construct the theoretical model. In this way, the model or the image data  18  can be built based upon image data acquired of the patient  14  with the imaging system  16 . The image acquisition control module  110  can output image data  18  to the display device  32   a  or the display device  20 . 
         [0049]    With reference to  FIG. 4 , a dataflow diagram illustrates various components of an image acquisition control system that can be embedded within the image acquisition control module  110 . The image acquisition control module  110  can control the imaging system  16  to generate the image data  18  for display on the display device  32   a  and/or display device  20 . Various embodiments of the image acquisition control system according to the present disclosure can include any number of sub-modules embedded within the image acquisition control module  110 . The sub-modules shown may be combined and/or further partitioned to similarly generate the image data  18 . Further, the image acquisition control module  110  can comprise one or more software modules embodied in non-transitory, machine readable code that runs on the processor  108 . Inputs to the system can be received from the input device  32   c , input device  24 , or even received from other control modules (not shown) within the computing system  22  or imaging computing system  32 , and/or determined by other sub-modules (not shown) within the image acquisition control module  110  (not shown). 
         [0050]    With continuing reference to  FIG. 4 , the image acquisition control module  110  can include an image control module  130 , a source control module  132  and a detector control module  134 . The image control module  130  can receive as input user input data  136 . The user input data  136  can comprise input received from the input device  32   c  or input device  22 . The user input data  136  can comprise a request for the imaging system  16  to perform a particular form of imaging. For example, the user input data  136  could comprise a request for the imaging system  16  to perform gated imaging. In another example, the user input data  136  could comprise a request for the imaging system  16  to perform dual energy imaging, or single energy imaging. Based on the user input data  136 , the image control module  130  can set source data  138  for the source control module  132 . The source data  138  can comprise a signal to start the imaging system  16 , a signal to power-down the imaging system  16 , a signal to perform gated imaging, a signal to perform dual energy imaging or a signal to perform single energy imaging. 
         [0051]    The image control module  130  can also receive as input detector data  140 . The detector data  140  can comprise the energy from the pulses  118   a - 118   n  received by the detector  38 . Based on the detector data  140 , the image control module  130  can set move data  142  for the source control module  132  and the move data  144  for the detector control module  134 . The move data  142  can comprise a signal for the source  36  to be moved to a predetermined angular position within the gantry  34  to acquire additional image data for the patient  14 . The move data  144  can comprise a signal for the detector  38  to be moved to a predetermined angular position within the gantry  34  relative to the source  36  to acquire additional image data for the patient  14 . The image control module  130  can also output the image data  18  based on the detector data  140 . The image data  18  can comprise the reconstructed 3D image of the patient. 
         [0052]    With continued reference to  FIG. 4 , the source control module  132  can receive as input the source data  138  and the move data  142  from the image control module  130 . Based on the move data  142 , the source  36  can move within the gantry  34  to a desired location. Based on the source data  138 , the source  36  can output pulse data  146 . The pulse data  146  can comprise at least one x-ray pulse, and in some instances can comprise more than one x-ray pulse, as will be discussed in greater detail herein. 
         [0053]    The detector control module  134  can receive as input the move data  144  and the detector data  140 . Based on the move data  144 , the detector  38  can move within the gantry  34  to a desired location relative to the location of the source  36 . The detector control module  134  can set the detector data  140  for the image control module  130 . 
         [0054]    With reference now to  FIG. 5 , a flowchart diagram illustrates an exemplary method performed by the image acquisition control module  110 . It should be noted that the flowchart diagram described herein with regard to  FIGS. 5-8  is merely exemplary, as the image acquisition control module  110  could generate the image data  18  in any desired or user requested sequence. With continued reference to  FIG. 5 , at decision block  200 , the method determines if a startup request signal has been received via the input device  32   c . If not, the method loops. Otherwise, the method goes to decision block  202 . 
         [0055]    At decision block  202 , the method determines if a type of energy output for the source  36  of the imaging system  16  has been specified. If a type of output for the source  36  has been specified, then the method goes to decision block  204 . Otherwise, the method loops. At decision block  204 , the method determines if the type of output for the source  36  is gated image acquisition. If the type of output for the source  36  is gated image acquisition, the method goes to A on  FIG. 6 . Otherwise, the method goes to decision block  206 . 
         [0056]    At decision block  206 , the method determines if the type of output for the source  36  is a single energy output. If the output for the source  36  is single energy imaging output, then the method goes to B on  FIG. 7 . Otherwise, the method goes to decision block  208 . At decision block  208 , the method determines if the output for the source  36  is dual energy output. If the output for the source  36  is dual energy output, then the method goes to C on  FIG. 8 . Otherwise, the method loops to decision block  202 . 
         [0057]    With reference to  FIG. 6 , at block  300 , the method acquires at least one physiological signal. Then, at decision block  302 , the method determines if a triggering event has occurred. If a triggering event has occurred, then the method goes to block  304 . Otherwise, the method loops until a triggering event has occurred. At block  304 , the method outputs a first pulse  118   a  at a first pulse rate. Then, at block  306 , the method acquires detector data  140  for the first pulse  118   a . At decision block  308 , the method determines if another triggering event has occurred. If another triggering event has occurred, then the method goes to block  310 . Otherwise, the method loops. 
         [0058]    At block  310 , the method outputs a second pulse  118   b  at a second pulse rate, which can have a different pulse width and height. The second pulse rate width and/or height can be greater than, less than or equal to the width and/or height of the first pulse rate. For example, the second pulse rate can have a second kilovolt (kV) value and a second width value in milliseconds (ms) and the first pulse rate can have a first kilovolt (kV) value and a first width value in milliseconds (ms), which may or may not be equal. In one example, the first kilovolt (kV) value can be from about 100 kV to about 120 kV, such as about 110 kV, and the second kilovolt (kV) value can be from about 70 kV to about 90 kV. The first width value can be from about 5 ms to about 15 ms, for example, about 10 ms, and the second current value can be from about 10 ms to about 20 ms, for example about 15 ms. 
         [0059]    At block  312 , the method acquires the detector data  140  for the second pulse  118   b . At block  314 , the method moves the source  36  and the detector  38 . Then, at decision block  316 , the method determines if enough image data has been acquired for the patient  14 . In this regard, the method can determine if the source  36 /detector  38  have gathered a suitable number of frames of image data to enable successful 3D reconstruction of the area of interest. In one example, the source  36 /detector  38  can acquire about 180 to about 240 frames of images, which can be substantially equivalent to gathering about 360° worth of image data, even if the source  36 /detector  38  does not fully circumscribe or travel 360° around the patient  14 . Based on gathered image data, the image acquisition control module  110  can perform automatic reconstruction of the area of interest. Further information regarding image acquisition techniques can be found in U.S. patent application Ser. No. 12/908,186, filed on Oct. 20, 2010, entitled “Selected Image Acquisition Technique to Optimize Patient Model Construction,” and incorporated by reference herein. 
         [0060]    If enough image data has been acquired for reconstruction, then the method goes to block  318 . Otherwise, the method loops to decision block  302 . At block  318 , the method compiles the detector data  140 . At block  320 , the method reconstructs the detector data  140  into the image data  18  using 3D reconstruction. At block  322 , the method outputs the image data  18  to the display device  32   a . At decision block  324 , the method determines if a power down request has been received via the input device  32   c . If a power down request has been received, the method ends. Otherwise, the method goes to D on  FIG. 5 . 
         [0061]    With reference to  FIG. 7 , at block  400 , the method outputs a pulse  118 . The pulse  118  can comprise a single pulse of energy, which can have a kilovolt (kV) value, which can be from about 80 kV to about 125 kV, The pulse width for this pulse  118  can range from about 5 ms to about 15 ms. Thus, the pulse  118  can have a wider pulse of smaller magnitude of current, which can be used in place of a larger magnitude of current pulse. 
         [0062]    At block  402 , the method acquires the detector data  140  for that pulse  118 . At block  404 , the method moves the source  36  and the detector  38 . At decision block  406 , the method determines if enough image data has been acquired for the patient  14 . If enough image data has been acquired for the patient  14 , then the method goes to block  408 . Otherwise, the method loops to block  400 . At block  408 , the method compiles the detector data  140 . At block  410 , the method reconstructs the detector data  140  into the image data  18  using 3D reconstruction. At block  412 , the method outputs the image data  18  to the display device  32   a . At decision block  414 , the method determines if a power down request has been received via the input device  32   c . If a power down request has been received, then the method ends. Otherwise, the method goes to D on  FIG. 5 . 
         [0063]    With reference to  FIGS. 8 and 9 , at block  500 , the method outputs a first pulse  118   a  at a first pulse rate having a first width and height and outputs a second pulse  118   b  at a second pulse rate having a second width and height. The second pulse rate width and/or height can be greater than, less than or equal to the first pulse rate width and/or height. For example, with reference to  FIG. 9 , the first pulse  118   a  can have a first kilovolt (kV) value  550  and a first width value  554  in milliseconds (ms). The second pulse  118   b  can have a second kilovolt (kV) value  556  and a second width value  560  in milliseconds (ms). 
         [0064]    In one example, the first kilovolt (kV) value  550  can be from about 90 kV to about 120 kV such as 110 kV, and the second kilovolt (kV) value  556  can be from about 70 kV to about 90 kV, such as 80 kV. The first pulse width  554  can range from about 5 ms to about 15 ms, for example 10 ms, while the second pulse width  560  can range from about 10 ms to about 20 ms, for example 15 ms. 
         [0065]    With reference back to  FIG. 8 , at block  502 , the method can acquire detector data  140  for the first pulse  118   a  and the second pulse  118   b . At block  504 , the method can move the source  36  and the detector  38  by a predetermined amount. At decision block  506 , the method can determine if enough image data has been acquired for the patient  14 . In this regard, the method can determine if the source  36 /detector  38  have gathered a suitable number of frames of image data to enable successful 3D reconstruction of the area of interest, as discussed with regard to  FIG. 6 . 
         [0066]    If enough image data has been acquired for the patient  14 , then the method goes to block  508 . Otherwise, the method goes to block  510 . At block  510 , the method waits a predetermined time period for the afterglow effects to subside before the method loops to block  500 . 
         [0067]    In this regard, each pulse  118  emitted by the source  36  causes the detector  38  to glow for a period of time after the pulse  118  has been emitted (“afterglow”). In cases where the first pulse  118   a  and the second pulse  118   b  have the same pulse rate (i.e. same kilovolts and same milliamps for the same period of time), the afterglow associated with each pulse  118   a ,  118   b  will be approximately the same except for the first pulse  118   a . As the afterglow is the same for each image, the effect of the afterglow can be removed from the image data  18  during processing thereby resulting in substantially undistorted image data  18 . In cases where the first pulse  118   a  and the second pulse  118   b  have different pulse rates, however, the afterglow associated with each pulse can vary, and thus, the effects of the afterglow cannot be easily removed from the image data  18 . Accordingly, by waiting a predetermined period of time before emitting another first pulse  118   a  and second pulse  118   b , the detector  38  can stop glowing, thereby substantially reducing the effects of the afterglow all together. With brief reference to  FIG. 9 , the predetermined time period between the emission of another first pulse  118   a  and second pulse  118   b  is illustrated with reference numeral  562 . 
         [0068]    With reference back to  FIG. 8 , at block  508 , the method can compile the detector data  140 . At block  512 , the method can reconstruct the detector data  140  into the image data  18  using 3D reconstruction. At block  514 , the method can output the image data  18  to the display device  32   a . At decision block  516 , the method can determine if a power down request has been received via the input device  32   c . If a power down request has been received, then the method ends. Otherwise, the method goes to D on  FIG. 5 . 
         [0069]    Thus, the image acquisition control module  110  can be used to optimize the acquisition of the image data  18  by the imaging system  16 . In addition, by enabling the user to select between gated image acquisition, single energy output and dual energy output from the source  36 , the image acquisition can be tailored to a particular patient  14 . With particular regard to gated image acquisition, the ability to gate the image acquisition to a particular physiological event can enable the user to view a selected organ of interest at a particular phase. The use of single energy output of a low current for a wider pulse width can enable a low-power generator, such as those associated with a mobile cart  30 , to acquire the image data  18  at the same quality and resolution as a high-power stationary generator. The use of dual energy output can optimize the acquisition of the image data  18  by providing high resolution imaging, without increasing the radiation dose received by the patient  14 . In addition, the image acquisition control module  110  can control the source  36  to emit dual energy pulses  118  without requiring a separate source  36 , detector  38  and gantry  34 . 
         [0070]    While specific examples have been described in the specification and illustrated in the drawings, it will be understood by those of ordinary skill in the art that various changes can be made and equivalents can be substituted for elements thereof without departing from the scope of the present teachings. Furthermore, the mixing and matching of features, elements and/or functions between various examples is expressly contemplated herein so that one of ordinary skill in the art would appreciate from the present teachings that features, elements and/or functions of one example can be incorporated into another example as appropriate, unless described otherwise, above. Moreover, many modifications can be made to adapt a particular situation or material to the present teachings without departing from the essential scope thereof. Therefore, it is intended that the present teachings not be limited to the particular examples illustrated by the drawings and described in the specification, but that the scope of the present teachings will include any embodiments falling within the foregoing description.