Abstract:
A method for calibrating detectors in a CT scanner, wherein the new calibration process uses a combination of slab-based and water-based calibrations. By combining both calibrations, the complexity of each procedure can be reduced which will reduce restrictions on the quality of detectors used in the scanner. The slabs can be made out of commercially available material such as acrylic, and they will require no special treatment. Combining both calibrations also reduces the number of water phantoms needed for the calibration and the complexity of the calibration algorithm. Furthermore, the slabs can be shaped based on the scanner geometry so as to optimize the slab-based calibration step.

Description:
REFERENCE TO PENDING PRIOR PATENT APPLICATION 
       [0001]    This patent application claims benefit of pending prior U.S. Provisional Patent Application Ser. No. 62/040,483, filed Aug. 22, 2014 by Neurologica Corp. and Ibrahim Bechwati et al. for ANATOMICAL IMAGING SYSTEM WITH IMPROVED DETECTOR CALIBRATION PROCESS (Attorney&#39;s Docket No. NEUROLOGICA-80 PROV), which patent application is hereby incorporated herein by reference. 
     
    
     FIELD OF THE INVENTION 
       [0002]    This invention relates to imaging systems in general, and more particularly to anatomical imaging systems. 
       BACKGROUND OF THE INVENTION 
       [0003]    In many situations it can be desirable to image the interior of opaque objects. By way of example but not limitation, in the medical field, it can be desirable to image the interior of a patient&#39;s body so as to allow viewing of internal structures without physically penetrating the skin. 
         [0004]    Computerized Tomography (CT) has emerged as a key imaging modality in the medical field. CT imaging systems generally operate by directing X-rays into the body from a variety of positions, detecting the X-rays passing through the body, and then processing the detected X-rays so as to build a three-dimensional (3D) data set and a 3D computer model of the patient&#39;s anatomy. The 3D data set and 3D computer model can then be visualized so as to provide images (e.g., slice images, 3D computer images, etc.) of the patient&#39;s anatomy. 
         [0005]    By way of example but not limitation, and looking now at  FIGS. 1 and 2 , there is shown an exemplary CT imaging system  5 . CT imaging system  5  generally comprises a torus  10  which is supported by a base  15 . A center opening  20  is formed in torus  10 . Center opening  20  receives the patient anatomy which is to be scanned. 
         [0006]    Looking next at  FIG. 3 , torus  10  generally comprises a fixed gantry  22 , a rotating disc  23 , an X-ray tube assembly  25  and an X-ray detector assembly  30 . More particularly, fixed gantry  22  is disposed concentrically about center opening  20 . Rotating disc  23  is rotatably mounted to fixed gantry  22 . X-ray tube assembly  25  and X-ray detector assembly  30  are mounted to rotating disc  23  in diametrically-opposing relation, such that an X-ray beam  40  (generated by X-ray tube assembly  25  and detected by X-ray detector assembly  30 ) is passed through the patient anatomy disposed in center opening  20 . Inasmuch as X-ray tube assembly  25  and X-ray detector assembly  30  are mounted on rotating disc  23  so that they are rotated concentrically about center opening  20 , X-ray beam  40  will be passed through the patient&#39;s anatomy along a full range of radial positions, so as to enable CT imaging system  5  to create a “slice” image of the anatomy penetrated by the X-ray beam. Furthermore, by moving the patient and CT imaging system  5  relative to one another during scanning, a series of slice images can be acquired, and thereafter appropriately processed, so as to create a 3D data set of the scanned anatomy and a 3D computer model of the scanned anatomy. In practice, it is common to configure X-ray detector assembly  30  so that multiple slices of images (e.g., 8 slices, 16 slices, 32 slices, etc.) may be acquired with each rotation of rotating disc  23 , whereby to speed up the acquisition of scan data. 
         [0007]    In practice, it is now common to effect helical scanning of the patient&#39;s anatomy so as to generate a 3D data set of the scanned anatomy, which can then be processed to build a 3D computer model of the scanned anatomy. The 3D data set and 3D computer model can then be visualized so as to provide images (e.g., slice images, 3D computer images, etc.) of the patient&#39;s anatomy. 
         [0008]    The various electronic hardware and software for controlling the operation of rotating disc  23 , X-ray tube assembly  25  and X-ray detector assembly  30 , as well as for processing the acquired scan data so as to generate the desired slice images, 3D data set and 3D computer model, may be of the sort well known in the art and may be located in torus  10  and/or base  15 . 
         [0009]    In many cases CT imaging system  5  is intended to be stationary, in which case base  15  of CT imaging system  5  is set in a fixed position on the floor of a room and a special motorized movable bed is provided to move the patient relative to CT imaging system  5  during scanning. More particularly, with a stationary CT imaging system  5 , the patient is brought to the location of CT imaging system  5 , the patient is placed on the motorized movable bed, and then the motorized movable bed is used to move the patient relative to CT imaging system  5  (i.e., to advance the patient into center opening  20  of CT imaging system  5 ) so that some or all of the length of the patient may be scanned by CT imaging system  5 . 
         [0010]    In other cases CT imaging system  5  is intended to be mobile so that the CT imaging system may be brought to the patient and the patient scanned at the patient&#39;s current location, rather than requiring that the patient be transported to the location of the CT imaging system. Scanning the patient with a mobile CT imaging system  5  can be highly advantageous, since it can reduce delays in patient scanning (e.g., the patient can be scanned in an emergency room rather than waiting to be transported to the radiology department) and/or it can allow the patient to be scanned without requiring movement of the patient (e.g., the patient can be scanned at their bedside in an intensive care unit, or “ICU”). To this end, and looking now at  FIGS. 4 and 5 , base  15  may comprise a transport assembly  50  for (i) moving mobile CT imaging system  5  to the patient prior to scanning and (ii) moving the CT imaging system relative to the patient during scanning. More particularly, transport assembly  50  preferably comprises (i) a gross movement mechanism  55  for moving CT imaging system  5  relatively quickly across room distances, so that the CT imaging system can be quickly and easily brought to the bedside of the patient, such that the patient can be scanned at their bedside without needing to be moved to the radiology department, and (ii) a fine movement mechanism  60  for moving the CT imaging system precisely, relative to the patient, during scanning so that the patient can be scanned on their bed or gurney without needing to be moved onto a special motorized movable bed. In one preferred form of the invention, gross movement mechanism  55  preferably comprises a plurality of free-rolling casters  62 , and fine movement mechanism  60  preferably comprises a plurality of centipede belt drives  63  (which can be configured for either stepped or continuous motion, whereby to provide either stepped or continuous scanning of the patient). Hydraulic apparatus  65  permits either gross movement mechanism  55  or fine movement mechanism  60  to be engaged with the floor, whereby to facilitate appropriate movement of mobile CT imaging system  5 . Thus, with a mobile CT imaging system  5 , the CT mobile imaging system may be pre-positioned in an “out of the way” location (e.g., in an unused corner of an emergency room) and then, when a patient requires scanning, the patient may be quickly and easily scanned at their bedside, by simply moving the mobile CT imaging system to the patient&#39;s bedside on gross movement mechanism  55  (e.g., casters  62 ), and thereafter moving the mobile CT imaging system during scanning on fine movement mechanism  60  (e.g., centipede belt drives  63 ). 
         [0011]    In current CT imaging systems, X-ray detector assembly  30  typically comprises solid state or ceramic detectors. 
         [0012]    A CT scanner equipped with solid state or ceramic detectors needs to be calibrated for two separate effects. The first is the calibration of the “beam hardening” effect due to the polychromatic nature of the X-ray spectrum. The second calibration is to compensate for variations in the spectral response of the detector caused by impurities in the detectors. Typically, the calibration process involves scanning well known materials (such as plastic or water) and determining an adjustment factor for each detector which reflects proper calibration for that detector. Some existing methods use cylindrical water phantoms of several diameters coupled with very complex mathematical procedures. Other calibration methods use solid slabs of well known materials. 
         [0013]    The advantage of the water calibration method is its ability to deal with a low grade material. However, a successful water-based calibration requires several water phantoms and a special calibration “seed” that needs to be generated manually and fine-tuned for each scanner. As such, water calibration is a lengthy procedure. 
         [0014]    Slab-based calibration is faster and requires a less complex mathematical algorithm. But the success of the slab-based calibration depends on the quality of the detector array, i.e., the similarity or the closeness of the spectral responses of the various detectors. This typically requires a costly process of “culling” detectors which significantly vary from a “norm”, which increases the cost of the detectors. Slab-based calibration also requires specially designed slabs that minimize the beam hardening effect through the material of the slab. 
         [0015]    Thus there is a need for an improved detector calibration process. 
       SUMMARY OF THE INVENTION 
       [0016]    These and other objects of the present invention are addressed by the provision and use of an improved detector calibration process. 
         [0017]    In the new detector calibration process, calibration is effected using a combination of both slab-based and water-based calibrations. By using a combination of both slab-based and water-based calibrations, the complexity of each calibration process can be reduced, which reduces restrictions on the quality of the detectors used in the scanner. The slabs can be made out of commercially available material (e.g., acrylic), and the slabs require no special treatment. Combining both slab-based and water-based calibrations also reduces the number of water phantoms needed for the calibration process and reduces the complexity of the calibration algorithm. Furthermore, the slabs can be shaped based in accordance with the scanner geometry so as to optimize the slab-based step in the calibration process. 
         [0018]    In one preferred form of the present invention, there is provided a method for calibrating detectors in a CT scanner, the method comprising: 
         [0019]    generating an initial set of calibration tables using a slab-based calibration process; and 
         [0020]    improving the initial set of calibration tables using a water-based calibration process. 
         [0021]    In another preferred form of the present invention, there is provided a method for calibrating detectors in a CT scanner, the method comprising: 
         [0022]    using a slab-based calibration step to generate slab-based correction coefficients; and 
         [0023]    using the slab-based correction coefficients from the slab-based calibration step as the seed in a water-based calibration step. 
     
    
     
       BRIEF DESCRIPTION OF THE DRAWINGS 
         [0024]    These and other objects and features of the present invention will be more fully disclosed or rendered obvious by the following detailed description of the preferred embodiments of the invention, which is to be considered together with the accompanying drawings wherein like numbers refer to like parts and further wherein: 
           [0025]      FIGS. 1 and 2  are schematic views showing the exterior of an exemplary CT imaging system; 
           [0026]      FIG. 3  is a schematic view showing various components in the torus of the exemplary CT imaging system shown in  FIGS. 1 and 2 ; 
           [0027]      FIGS. 4 and 5  are schematic views showing an exemplary transport assembly for an exemplary CT imaging system; 
           [0028]      FIG. 6  is a schematic view of the non-linear calibration process of the present invention; 
           [0029]      FIG. 7  shows the steps of the slab-based calibration process; 
           [0030]      FIG. 8  shows the various types of slab phantoms; 
           [0031]      FIG. 9  shows the positioning of the slabs in the X-ray fan beam; 
           [0032]      FIG. 10  shows the attenuation of an X-ray through a slab of width l and an attenuation μ; 
           [0033]      FIG. 11  shows the generation of the slab attenuation μl using the measured X-ray count; 
           [0034]      FIG. 12  shows the generation of slab coefficients; 
           [0035]      FIG. 13  shows the measured attenuation of the slab phantom; 
           [0036]      FIG. 14  shows the ideal and the measured slab data; 
           [0037]      FIG. 15  shows the ideal versus the corrected or measured slab data; 
           [0038]      FIGS. 16 and 17  show individual cylinders and interlocked cylindrical water phantoms; 
           [0039]      FIGS. 18 and 19  shows some possible placements of small and large water phantoms in the scanner field of view; 
           [0040]      FIG. 20  shows the block diagram of the slab corrected water data; 
           [0041]      FIG. 21  shows the block diagram of the process of generating the ideal water data; 
           [0042]      FIG. 22  shows the original and ideal attenuation data; 
           [0043]      FIG. 23  shows the measured versus the ideal data of a given detector using several water data; 
           [0044]      FIG. 24  shows the process of adjusting the slab-based correction coefficients using the water data; and 
           [0045]      FIG. 25  shows the adjustment coefficients. 
       
    
    
     DETAILED DESCRIPTION OF THE PREFERRED EMBODIMENTS 
       [0046]    In accordance with the present invention, there is provided an improved detector calibration process. 
         [0047]    The New Detector Calibration Process in General 
         [0048]    The new detector calibration process of the present invention combines slab-based calibration and the water-based calibration to reduce the complexity of the calibration process. The slab-based calibration step is used first to automatically generate the initial calibration tables for the subsequent water-based calibration step. The calibration tables produced by the slab-based calibration step replaces the manually generated “seed” traditionally used in the water-based calibration step. The slab-based calibration tables are generated according to the scanner. The slab-based calibration tables improve the subsequent water-based calibration step and reduce the number of water phantoms needed for the water-based calibration step and reduce the complexity of the calibration algorithm. 
         [0049]    The slab-based calibration step comprises acquiring data using a set of slab phantoms. The data is then processed to generate the corrected attenuation data of the slab phantoms. The corrected attenuation data is then averaged so as to create a measured profile of the slab phantoms. Using the knowledge-based information about the slab, an ideal profile is generated using a combination of linear fitting and data smoothing. The averaged measured profile is then compared to the ideal profile of the entire slab phantom for each detector. Later, a polynomial correction (e.g., a second order polynomial correction) is generated using the ideal profile and the measured slab data. The coefficients of the polynomial correction are then stored in calibration tables and used as the “seed” for the next calibration step (i.e., the water-based calibration step). 
         [0050]    The water-based calibration step begins with the acquisition of the water data phantoms. The data of the water phantoms is acquired at different locations in the scan field of view. The acquired data is then post-processed to generate attenuation profiles. The attenuation data is corrected using the calibration tables generated by the previous slab-based calibration step. Using the scanned data, an ideal profile is generated using fan beam re-projection. For each detector, the ideal and measured data is gathered using acquired data from all acquired water phantoms. The data is then compared and, using a first order or a second order polynomial fit, the data is fitted and the second order coefficients (generated earlier by the slab-based calibration step) are adjusted using the coefficients generated by the water-based calibration step so as to produce the final calibration tables. 
         [0051]      FIG. 6  is a schematic view of the non-linear calibration process of the present invention. The first step in the calibration process is the slab-based calibration step; the output of the slab-based calibration step is then used in the water-based calibration step for generating the final calibration tables (which are used to calibrate the detectors). 
         [0052]    1. The Slab-Based Calibration Step 
         [0053]    The slab-based calibration step comprises a data acquisition phase using specially designed slab phantoms. The acquired slab data is then processed to generate the slab tables.  FIG. 7  shows the steps of the slab-based calibration process. 
         [0054]    1.1 the Slab Phantoms 
         [0055]    The slab phantoms consist of multiple slabs made of the same material. It is preferable to choose a material that has similar properties to those of soft tissues, for example, the slabs can be made of “plastic water” (i.e., a plastic material chemically-altered to match the physical characteristics of water), acrylic, plastic or any other material. A thin piece of metal such as copper or aluminum can be taped to one side of the slab in order to “harden” the X-ray beam which passes through the slab. The slabs are typically made of rectangular pieces that can be stacked together. The slabs can be also be cut to match the scanner geometry, specifically, the scanner fan angles. Finally, the slabs can be shaped so as to generate the same path to each detector.  FIG. 8  shows various exemplary slab phantoms. 
         [0056]    1.2 the Positioning of the Slab Phantoms 
         [0057]    The slabs can be placed in vertical or horizontal positions. The slabs can be positioned using a specially design slab holder that helps position the slabs. The slabs can also be positioned on top of the collimator, or on a patient table or in a phantom holder. The slabs have to be wide enough to cover the entire detector array, whether they are positioned vertically or horizontally.  FIG. 9  shows the positioning of the slabs in the X-ray fan beam. 
         [0058]    1.3 the Data Acquisition Step 
         [0059]    The following data sets are acquired for each scan voltage and, optionally, for each collimation. It is important that the slab data be acquired without rotating the scanner gantry. 
         [0060]    In a “first method”, the slab raw data is acquired in what is known as “Service Mode”. The data acquisition consists of the following steps: 
         [0061]    1. Offset data: acquired in the absence of X-rays, the scan time should be at least as long as the time it takes for 3 rotations of the scanner gantry (when the scanner gantry is rotating). 
         [0062]    2. Air data: acquired with the X-ray tube on, using low scan current in the absence of any object obstructing the X-ray beam. The scan should be at least as long as the time it takes for 3 rotations of the scanner gantry (when the scanner gantry is rotating). 
         [0063]    3. The slab data: acquired with the X-ray tube on, the slab is positioned between the X-ray tube and the detector array. The scan current will be variable, dependent on the thickness of the slab. 
         [0064]    In a “second method”, the slab data acquisition is also done in Service Mode, however, the objective is to obtain attenuation data. The attenuation data can be acquired as follows: 
         [0065]    1. Run the daily air calibration on the scanner. 
         [0066]    2. Load a set of Null calibration tables. 
         [0067]    3. Scan the slab in image mode without rotating the gantry. 
         [0068]    4. The corrected slab data is then extracted from the scanner and used for the calibration. 
         [0069]    In the aforementioned “first method” the acquired data is a function of the photon counts, 
         [0000]    
       
      
       I 
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         [0000]    where I meas  is the measured raw data, I 0  is the intensity of the X-ray beam from the source and μl is the linear attenuation of the measured slab.  FIG. 10  shows the attenuation of the X-ray through a slab of width  1  and an attenuation μ. 
         [0070]    The aforementioned “second method” measures the attenuation μl. 
         [0071]    1.4 Slab Data Post Processing 
         [0072]    The data post-processing step creates the attenuation data through the data correction process, using the raw data acquired in the first data acquisition method discussed in Section 1.3 above. The attenuation data is obtained as follows, for each acquired view: 
         [0073]    1. Create an offset table using the offset data: O(d) is the calibrated offset of the d th  detector. 
         [0074]    2. Create an air table using the offset tables and the air data. A(d) is the calibrated gain of the d th  detector. 
         [0075]    3. Correct the raw slab data for offset: S o (d)=S r (d)−O(d), where S o (d) is the offset corrected slab data of the d th  detector, and S r (d) the acquired raw data of the d th  detector. 
         [0076]    4. Compute the log of the offset corrected data: S t (d)=log(S o (d)). 
         [0077]    5. Correct the logged data using the reference data: S R  (d)=s I (d)−log(ref) 
         [0078]    6. Correct the logged data using the air table. S a (d)=A(d)−S R (d), S a (d) is the gain corrected logged data. 
         [0079]    7. The attenuation of the slab is the gain corrected slab data: μl(d)=S a (d). 
         [0080]    8. The slab attenuation data is also corrected for beam hardening. 
         [0081]      FIG. 11  shows the generation of the slab attenuation μl using the measured X-ray count.  FIG. 12  shows the generation of slab coefficients.  FIG. 13  shows the measured attenuation of the slab phantom. 
         [0082]    The aforementioned post processing step can be omitted if the data is acquired using the second acquisition method discussed in Section 1.3 above. 
         [0083]    1.5 Generating the Slab Attenuation Profiles 
         [0084]    The attenuation slab data is then processed to create an attenuation profile for each slab. The profile is obtained by averaging the corrected data over all the acquired views: 
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         [0000]    where is the averaged attenuation data of the d th  detector, N v  is the number of acquired views, and μl i   m (d) is the corrected measured attenuation of the i th  view and the d th  detector.  FIG. 13  shows the averaged attenuation profile of the slab. Based on the type of the slab phantom, the data may be normalized based on the X-ray path through the slab. The normalized attenuation is computed as follow: 
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         [0000]    where y(d) is the angle of the d th  detector.  FIG. 13  shows the averaged slab data (curved) and the normalized slab data (straight). 
         [0085]    1.6 Generate the Ideal Slab Attenuation 
         [0086]    An ideal profile of the slab is generated using either a linear fitting approach or a low-pass filter approach. The linear fitting approach is typically done using a Minimum Mean Square Estimate (MMSE): 
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         [0087]    Using linear fitting, an ideal slab profile is computed using the MMSE method. The ideal slab profile can also be generated using a low-pass filter approach, the ideal profile is estimated as follow: 
         [0088]      FIG. 14  shows the ideal and the measured slab data. 
         [0089]    1.7 Extract the Measured and the Ideal Slab Data 
         [0090]    The measured and the ideal slab data is extracted for each detector. For a given detector, the following two sets of data are extracted from both the measured and the estimated ideal data: 
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         [0000]    where l is the slab index; l=0, . . . , N s , and where N s  is the number of slabs used in the calibration. 
         [0091]      FIG. 15  shows the ideal versus the corrected or measured slab data. 
         [0092]    1.8 Compute the Slab-Based Calibration Correction Coefficients 
         [0093]    The measured data of each detector is then “fitted” using a polynomial fit, and the correction coefficients are computed as the slab-based correction coefficients, a i , are obtained using a second degree polynomial fit: 
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         [0094]    2. The Water-Based Calibration Step 
         [0095]    The water-based calibration step can also be considered to be the slab-based coefficient adjustment step using the water phantoms. The water-based calibration step uses the data from the water phantoms to adjust the slab-based correction coefficients generated previously during the slab-based calibration step. 
         [0096]    2.1 the Water Phantoms 
         [0097]    Water cylinders of several diameters can be used in the adjustment process. Ideally, the set of water phantoms should cover the attenuation range of a typical patient. The set of water phantoms consists of water cylinders with diameters ranging from 10 cm to 40 cm. The set can be made of individual cylinders or interlocked cylinders.  FIG. 16  shows individual cylinders, and  FIG. 17  shows interlocked cylindrical water phantoms. The water cylinder is typically made of acrylic. 
         [0098]    2.2 the Positioning of the Water Phantoms 
         [0099]    The water phantoms are positioned at different locations in the scan field of view based on their size. The main objective of positioning the water phantoms at different locations is to increase the detector coverage using different attenuation levels. Water phantoms with smaller diameters are placed at several locations in the scan field of view, typically, a centered position and two off-centered positions. Water phantoms with larger diameters may only need to be positioned twice in the field of view, a centered position and an off-centered position. Unlike other methods of detector calibration, where the water phantom positions are well defined and small tolerances are given for their placement, the new detector calibration process of the present invention does not require specific placement of the water phantoms. The water adjustment places no constraints on the positioning of the water phantoms in the scan field of views.  FIGS. 18 and 19  shows some possible placements of small and large water phantoms in the scanner field of view. 
         [0100]    2.3 The Data Acquisition 
         [0101]    The water phantom data can be acquired in two different modes: “raw data acquisition mode”, and “attenuation data correction mode”. In both cases, the data is acquired in rotating mode, i.e., the gantry is rotating. 
         [0102]    In the “raw data acquisition mode”, only data is acquired and processing is accomplished using off-line computers: 
         [0103]    1. Offset data: the data is acquired in the absence of X-rays; the data should be acquired over at least three rotations of the scanner gantry. 
         [0104]    2. Air data: The data is acquired with the X-ray tube on, in the absence of any object in the scanner field of view. The scan current should be in the low 50&#39;s (mA) and the data should be acquired over at least three rotations of the scanner gantry. 
         [0105]    3. Water phantom data: The data is acquired with the X-ray tube on; the water phantom is placed in the scanner field of view. The data should cover at least four rotations of the scanner gantry. The scan current depends on the size of the water phantom. A scan current in the scanner mid-range can be used for small water phantoms, e.g., phantoms with less than 20 cm diameter can be scanned using a 200 mA scan current. Larger water phantoms should be scanned at the upper-range of the scan current, e.g., a 200 to 300 mA scan current. 
         [0106]    In the “attenuation data correction mode”, the corrected data is extracted from the scanner and used in the adjustment of the initial slab-based correction coefficients: 
         [0107]    1. Load the initial slab-based correction coefficient onto the scanner. 
         [0108]    2. Set the acquisition parameters of a given scan, i.e., scan voltage, scan collimation, scan current and the scan time. 
         [0109]    3. Complete the scan. 
         [0110]    4. Review the scanned images. 
         [0111]    5. Store the corrected data and the image data. 
         [0112]    The scan time and the scan current can be adjusted for different scanners. The key objective is to collect enough statistical data to generate a reliable estimate of the differential gain error of the detectors. 
         [0113]    2.4 The Data Post-Processing 
         [0114]    Data post-processing will differ based on the data acquisition mode. 
         [0115]    Where the data is acquired in the aforementioned “raw data acquisition mode” (see Section 2.3 above): 
         [0116]    1. Create an offset table using the offset data: O(d) is the calibrated offset of the d th  detector. 
         [0117]    2. Create an air table using the offset tables and the air data. A(d) is the calibrated gain of the d th  detector. 
         [0118]    3. Correct the raw phantom data for offset: W o (d)=W r (d)−O(d), where W o (d) is the offset corrected water data of the d th  detector, and W r (d) is the acquired raw data of the d th  detector. 
         [0119]    4. Compute the log of the offset corrected data: W I (d)=log (W O (d)) 
         [0120]    5. Correct the logged data using the reference data: W R (d)=W I (d)−log(ref). 
         [0121]    6. Correct the logged reference corrected data using the air table. W a (d)=A(d)−W R (d), where W a (d) is the gain corrected logged data. 
         [0122]    7. The uncorrected attenuation of the water is the gain corrected slab data: μl w (d)=W a (d). 
         [0123]    8. Correct the gain corrected data for beam hardening: 
         [0000]      μ l   w   b ( d )=Σ all BHC   b   i (μ l   w ( d )) s  
 
         [0124]    9. Correct the water attenuation using the initial slab-based correction coefficients: 
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         [0125]    In the aforementioned “attenuation data correction mode” (see Section 2.3 above), the post-processing step is accomplished by the scanner. The corrected attenuation data is simply extracted from the scanner. Once the attenuation data of the acquired water phantoms is generated, they are stored. The next step is to generate a set of ideal attenuation. The corrected attenuation and the ideal attenuation are compared.  FIG. 20  shows the block diagram of the slab corrected water data. 
         [0126]    2.5 Generating the Ideal Water Data 
         [0127]    The ideal water data is generated using the acquired water phantom data. The basic idea is to replace the “raw” water data with “ideal” data and generate the ideal data for each detector. The efficiency of the adjustment depends on the original correction coefficients and the location of the water phantom. Prior methods require knowledge of the exact location of the water phantom relative to the detector. With the novel detector calibration process of the present invention, generating the ideal water data does not require a prior knowledge of the position of the water phantom relative to the detector. Generating the ideal water data of a given detector is described below: 
         [0128]    1. Generate full field of view images of the water phantoms using the post-processed data. 
         [0129]    2. Automatically locate the water phantom in the scan field of view. 
         [0130]    3. Replace only the water inside the image using the ideal CT value of water. 
         [0131]    4. Adjust the value of the image background. 
         [0132]    5. Recreate the ideal attenuation data by re-projecting the ideal images using the exact model of the scanner. 
         [0133]    6. Repeat for all acquired data. 
         [0134]      FIG. 21  shows the block diagram of the process of generating the ideal water data.  FIG. 22  shows the original and ideal attenuation data. 
         [0135]    2.6 Extracting the Measured Data and the Ideal Data of a Given Detector 
         [0136]    The measured data and the ideal data are extracted for each detector. The data is extracted from each water phantom used in the acquisition.  FIG. 23  shows the measured versus the ideal data of a given detector using several water data. 
         [0137]    2.7 Computing the Adjustment Coefficient 
         [0138]    Using the extracted data of each detector, a set of adjustment coefficients are generated using polynomial fitting. Several methods can be used to generate the correction coefficients. One method of generating the correction coefficients uses the Minimum Mean Square Estimate (MMSE).  FIG. 24  shows the process of adjusting the slab-based correction coefficients using the water data. 
         [0139]    2.8 Adjusting the Slab-Based Correction Coefficients 
         [0140]    The water-based adjustment coefficients generated earlier are used to adjust the slab-based correction coefficient. The step can be omitted here and applied later during the data correction step.  FIG. 25  shows the adjustment coefficients. 
         [0141]    Application to Other Types of Scanning Systems 
         [0142]    It should be appreciated that the present invention is not limited to use in medical applications. Thus, for example, the present invention may be used in connection with CT machines used for non-medical applications, e.g., with CT machines used to scan inanimate objects. 
       Modifications 
       [0143]    It will be appreciated that still further embodiments of the present invention will be apparent to those skilled in the art in view of the present disclosure. It is to be understood that the present invention is by no means limited to the particular constructions herein disclosed and/or shown in the drawings, but also comprises any modifications or equivalents within the scope of the invention.