EP1021128A1 - Detection de cible par tomographie assistee par ordinateur - Google Patents

Detection de cible par tomographie assistee par ordinateur

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Publication number
EP1021128A1
EP1021128A1 EP19980948103 EP98948103A EP1021128A1 EP 1021128 A1 EP1021128 A1 EP 1021128A1 EP 19980948103 EP19980948103 EP 19980948103 EP 98948103 A EP98948103 A EP 98948103A EP 1021128 A1 EP1021128 A1 EP 1021128A1
Authority
EP
European Patent Office
Prior art keywords
data
region
projection
image
slice
Prior art date
Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
Withdrawn
Application number
EP19980948103
Other languages
German (de)
English (en)
Inventor
Carl R. Crawford
Eric Bailey
Alexander I. Greenberg
Christopher C. Ruth
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Analogic Corp
Original Assignee
Analogic Corp
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Priority claimed from US08/948,697 external-priority patent/US5887047A/en
Application filed by Analogic Corp filed Critical Analogic Corp
Publication of EP1021128A1 publication Critical patent/EP1021128A1/fr
Withdrawn legal-status Critical Current

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Classifications

    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/02—Arrangements for diagnosis sequentially in different planes; Stereoscopic radiation diagnosis
    • A61B6/03—Computed tomography [CT]
    • A61B6/032—Transmission computed tomography [CT]
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/02—Arrangements for diagnosis sequentially in different planes; Stereoscopic radiation diagnosis
    • A61B6/027—Arrangements for diagnosis sequentially in different planes; Stereoscopic radiation diagnosis characterised by the use of a particular data acquisition trajectory, e.g. helical or spiral
    • A—HUMAN NECESSITIES
    • A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
    • A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
    • A61B6/00—Apparatus or devices for radiation diagnosis; Apparatus or devices for radiation diagnosis combined with radiation therapy equipment
    • A61B6/52—Devices using data or image processing specially adapted for radiation diagnosis
    • A61B6/5258—Devices using data or image processing specially adapted for radiation diagnosis involving detection or reduction of artifacts or noise
    • G—PHYSICS
    • G06—COMPUTING; CALCULATING OR COUNTING
    • G06T—IMAGE DATA PROCESSING OR GENERATION, IN GENERAL
    • G06T11/00—2D [Two Dimensional] image generation
    • G06T11/003—Reconstruction from projections, e.g. tomography
    • G06T11/005—Specific pre-processing for tomographic reconstruction, e.g. calibration, source positioning, rebinning, scatter correction, retrospective gating

Definitions

  • the present invention relates generally to computed tomography (CT) imaging and more particularly to CT imaging with improved efficiency and reduced image artifacts.
  • CT computed tomography
  • FIG. 1 is a schematic axial view of a typical conventional CT scanner 10 which includes an x-ray source 12 and an x-ray detector system 14 secured to diametrically opposite sides of an annular shaped disk 16.
  • the disk 16 is rotatably mounted within a gantry support (not shown), so that during a scan the disk 16 continuously rotates about a z-axis while x-rays pass from the source 12 through an object, such as a patient 20 positioned on a patient table 56 within the opening of the disk 16.
  • the z-axis is normal to the plane of the page in FIG. 1 and intersects the scanning plane at the mechanical center of rotation 18 of the disk 16.
  • the mechanical center of rotation 18 of the disk corresponds to the "isocenter" of the reconstructed image.
  • the detector system 14 includes an array of individual detectors 22 disposed in a single row in a shape of an arc having a center of curvature at the point 24, referred to as the "focal spot," where the radiation emanates from the x-ray source 12.
  • the source 12 and array of detectors 22 are positioned so that the x-ray paths between the source and each detector all lie in a "scanning plane" that is normal to the z-axis. Since the x-ray paths originate from what is substantially a point source and extend at different angles to the detectors, the x-ray paths form a "fan beam" 26 that is incident on the detector array 14 in the form of one-dimensional linear projection.
  • each detector generates an output signal indicative of the intensity of its corresponding ray. Since each ray is partially attenuated by all the mass in its path, the output signal generated by each detector is representative of the attenuation of all the mass disposed between that detector and the X-ray source, i.e., the attenuation of the mass lying in the detector's corresponding ray path.
  • the output signals generated by the X-ray detectors are normally processed by a signal processing portion (not shown) of the CT system.
  • the signal processing portion generally includes a data acquisition system (DAS) which filters the output signals generated by the X-ray detectors to improve their signal-to-noise ratio (SNR).
  • DAS data acquisition system
  • SNR signal-to-noise ratio
  • the output signals generated by the DAS during a measuring interval are commonly referred to as a “projection” or “view” and the angular orientation of the disk 16, source 12 and detector system 14 corresponding to a particular projection is referred to as the "projection angle.
  • FIG. 2 illustrates the orientation of the disk 16, X-ray source 12 and detector system 14 for generation of a fan beam data point P f ( ⁇ , ⁇ ) at a projection angle ⁇ and a detector angle ⁇ .
  • a center line 40 which is used to define reference orientations, extends from the focal spot of the X-ray source 12 through the z-axis at the mechanical center of rotation 18.
  • the projection angle ⁇ is defined as the angle between a vertical axis and the center line 40.
  • Each individual detector in system 14 has an associated detector angle ⁇ that is also defined with respect to the center line 40.
  • the center line 40 intersects the detector system 14 at a reference detector angle ⁇ of 0°.
  • a symmetric detector system 14 as shown in FIG.
  • a fan beam view or projection P f ( ⁇ , ⁇ ) generated by symmetric detector system 14 includes a set of data points P f ( ⁇ , ⁇ ), generated by all the detectors at the detector angles from - ⁇ to + ⁇ for the projection angle ⁇ .
  • Asymmetric detector systems are also well known.
  • the disk 16 rotates smoothly and continuously around the object being scanned, allowing the scanner 10 to generate a set of projections P ⁇ , ⁇ ) at the corresponding set of projection angles ⁇ .
  • the patient remains at the constant z-axis position during the scan.
  • the patient is stepped along the z-axis between scans.
  • CZA constant-z- axis
  • a tomogram is a representation of the density of a two-dimensional slice along the slice plane of the object being scanned.
  • the process of generating a tomogram from the projections is commonly referred to as "reconstruction, " since the tomogram may be thought of as being reconstructed from the projection data.
  • the reconstruction process can include several steps including convolution to deblur the data, rebinning to form parallel-ray data from the fan-beam-ray data and back projection in which image data for each image pixel is generated from the projection data.
  • CZA scanning for a particular image slice, all the projections share a common scanning plane, so these projections may be applied directly to the back projector for generation of a tomogram.
  • the step-and-shoot CZA scanning approach can be a slow process. During this time consuming approach, the patient can be exposed to high amounts of X-ray radiation. Also, as the scanning table is moved between each scan, patient motion can result, causing motion and misregistration artifacts which result in reduced image quality.
  • CSH constant-speed-helical
  • FIG. 3A illustrates the data collected during a conventional CZA scan
  • FIG. 3B illustrates the data collected during a CSH scan.
  • the scanning planes associated with all the projections collected by the detector system 14 will all lie in a common slice plane 50.
  • FIG. 3B if the object 20 is continuously translated in the direction of the z-axis while the disk is rotated about the object 20, none of the scanning planes will be co-planar.
  • each projection will lie at a unique position along the z-axis at a locus point on a helical set of loci.
  • FIG. 3B illustrates the z-axis coordinate of the scanning planes corresponding to helical projection angles in the interval (0, lO ⁇ ). Since the value of each projection depends on the z-axis location of the patient, each projection may be considered a function of two variables ⁇ and z.
  • each projection has a unique scanning plane located at a unique z-axis coordinate, so CSH projections may not be applied directly to a back projector.
  • the data collected during a CSH scan can be interpolated in various fashions to generate a set of interpolated projections that do all share a common scanning plane extending normal to the z-axis.
  • Each interpolated projection for example, may be generated by combining two projections taken at equivalent projection angles and at different z-axis positions.
  • interpolated projections may be treated as CZA data and applied to a back projector to generate a tomogram.
  • CSH scanning requires some form of interpolation to generate a tomogram, and tomograms generated by CSH scanning therefore tend to be characterized by image artifacts.
  • the CSH scan projection data which are collected over an interval of z-axis locations, are combined to generate the interpolated CZA scan data, tomograms generated during CSH scanning have a wider effective slice plane width and, therefore, lower z-axis resolution, than tomograms generated by CZA scanning.
  • helical scanning advantageously permits rapid scanning of a large volume of a patient.
  • a helical scan can collect enough data to fully scan an entire organ such as a kidney.
  • CZA scanning Another approach to decreasing scan time over CZA scanning is commonly referred to as "cone-beam scanning, " in which a three-dimensional volume of the object or patient is scanned at once.
  • cone-beam scanning the detection system includes a two-dimensional array of detectors instead of the one-dimensional array used in conventional scanning.
  • the X-ray output from the source diverges in two dimensions to produce the equivalent of multiple fan beams along the z-axis dimension which illuminate multiple rows of plural detectors and therefore form a two-dimensional projection on the array.
  • a cone-beam system In one form of a cone-beam system, the patient or object is maintained in a stationary z-axis position while the source and two-dimensional detector array are rotated around the patient or object. The patient is then moved to a new z-axis position, and the scan is repeated.
  • a volume of the object is scanned. After one volume is scanned, the source and detector are stepped along the z-axis to scan the next volume.
  • HLB helical cone-beam
  • Standard two-dimensional reconstruction techniques such as 2D filtered back projection (FBP) are used to reconstruct CZA and interpolated CSH data in non-cone-beam systems.
  • FBP requires that the set of projections used for reconstruction lie in the same plane. This condition is satisfied in CZA scanning, and interpolation is used in CSH scanning to produce a set of interpolated or simulated linear projections which effectively meet this requirement.
  • 2D FBP is an efficient means of producing image data from the ID fan-beam projection data.
  • cone-beam geometry In cone-beam geometry, the required condition is only satisfied for a detector row coplanar with the source in a plane perpendicular to the z-axis, i.e., the center detector row.
  • a ID projection defined by the source and a given detector row will intersect a different slice in the object as the gantry rotates.
  • Conventional 2D FBP can be used to reconstruct cone-beam data by treating each row as an independent ID projection. This approximation ignores the cone-beam geometry and results in image artifacts such as streaks and lowering of the reconstructed density.
  • a better approximate method used to reconstruct cone-beam data is known as the Feldkamp algorithm and is described in L. A. Feldkamp, et ⁇ .," Practical cone-beam algorithm, " J. Opt. Soc. Am. I, pp. 612-619, (1984).
  • CT scanning is applicable to identification of contraband items, such as weapons and explosives in baggage being carried or loaded onto commercial aircraft. It is often desirable to pre-screen baggage to identify suspect bags which can then be subject to full CT image reconstruction if the pre-screening process identifies a suspect target.
  • a separate line scanner is used to generate a two-dimensional projection through the object being scanned, e.g., patient baggage, to identify suspect areas. Where a suspect target is identified, the object can then be subjected to full CT scanning and reconstruction. This process can be time consuming and, in the baggage scanning application, can be impractical, considering the rate at which bags must be screened at a commercial airport.
  • Another object of the invention is to provide a CT system with reduced image artifacts.
  • Yet another object of the invention is to provide a CT system which provides the image quality of a three-dimensional reconstruction algorithm using two-dimensional reconstruction hardware.
  • Still another object of the invention is to realize the foregoing objects in a helical cone-beam scanning CT system.
  • the present invention is directed to a CT apparatus and method for generating image data for a region.
  • the region defines a longitudinal axis and an orthogonal transverse axis.
  • a radiation source and an array of detectors are used to scan the region to generate scanned data that is representative of the region.
  • a helical cone-beam scanning approach is used to scan the region.
  • a two-dimensional image data slice is defined. Each data slice defines a slice plane which is tilted with respect to the longitudinal axis of the region.
  • the normal axis of each slice plane is tilted at a tilt angle with respect to the longitudinal axis of the region.
  • the normal axis also defines a rotation angle with the transverse axis of the region.
  • Successive slices along the longitudinal axis define normal axes that define equal tilt angles with the longitudinal axis of the region.
  • the rotation angle for successive slices increases along the longitudinal axis.
  • the result of the constant tilt angle and increase in rotation angle is that the normal axes describe a precession and nutation about the longitudinal axis of the region through successive slices.
  • the slices can be said to be nutated with respect to each other.
  • image data is computed from the scan data to produce the image of the region.
  • the reconstruction process for successive slices is hereinafter referred to as the "nutating slice reconstruction" (NSR) approach.
  • the NSR approach of the invention is preferably used to reconstruct helical cone-beam data using conventional two-dimensional filtered back projection.
  • NSR a set of ID fan-beam projections is extracted from the 2D cone-beam projection data set using interpolation. NSR therefore involves the selection of 2D fan-beam data from 3D cone-beam data.
  • the ID projection set corresponds to reconstructing a tilted slice whose geometry is chosen to minimize the adverse effects of the cone angle on image quality when using 2D FBP.
  • each slice is the x-y plane at a different location along the z-axis. That is, all the slices in the series are parallel to each other.
  • NSR the normal vector to the reconstructed slice plane is tilted by a small angle with respect to the z-axis.
  • the normal vector to the slice plane precesses about the z- axis and the slices are not parallel to each other.
  • the term "nutated" in NSR refers to the relative orientation of adjacent slices. If parallel slices are required, the resultant NSR image data can be interpolated to provide parallel slices.
  • the x-ray source is a cone-beam source
  • the array of detectors is a two-dimensional array.
  • the scan data for each projection is determined from a predefined one-dimensional line of detectors on the array.
  • the detectors used for a given projection or slice are associated with the projection angle or position along the longitudinal axis. At each position or projection angle, a group of detectors is chosen which minimizes the error in the measurement.
  • Each slice is therefore associated with a projection angle, a longitudinal position and a group of detectors which in general defines a one-dimensional "fan-beam" projection on the two-dimensional detector array.
  • the invention is directed to an apparatus and method for providing a two-dimensional projection image of a region from the scan data generated for the region.
  • Each nutated slice is generated from a set of fan beam views or projections which are rebinned to parallel-ray projection data, with each view or projection being obtained at a respective view angle.
  • a projection angle for the two-dimensional projection image is selected as the angle at which the two-dimensional projection image is to be taken.
  • the view angle associated with the selected projection angle is identified, and the parallel-ray projection data associated with that view angle is selected.
  • the two-dimensional projection image at the selected projection angle is generated by combining the selected parallel-ray projection data for the selected view angle for each slice in the scan data.
  • multiple two-dimensional projection images can be generated at multiple projection angles. These multiple projection images can be generated from a single set of scan data.
  • the length of the projection image along the z-axis is equal to the axial extent of the slices used to form the projection image.
  • the two-dimensional projection image can be used to determine the size of an object projected at the selected projection angle. By identifying object boundaries in the two-dimensional projection image, the size of the object and its location within the field of view can be determined. The object size and location can also then be used to identify the object and to identify regions of the field of view that need not be reconstructed since they provide no information regarding the object.
  • This "adaptive field of view” can be very useful in systems in which scanning throughput is important, such as in a baggage scanning system. This feature is described and claimed in a U.S. patent application entitled “Computed Tomography Scanning Apparatus and Method Using Adaptive Reconstruction Window," by Bernard M. Gordon, et al. (Attorney Docket No. ANA- 136), filed on even date herewith, of common assignee and incorporated herein by reference.
  • the invention is directed to a method and apparatus for detecting targets such as explosives using the nutated image slices generated in accordance with the nutating slice reconstruction approach of the invention.
  • tilt or nutation of the slices is compensated for to provide accurate target identifications.
  • Scan data for a region in which an object is located are obtained by scanning the region with a radiation source and an array of detectors. Using the scan data, a plurality of non-parallel image data slices are defined to correspond with a plurality of positions along the longitudinal axis of the region.
  • Each slice defines a plurality of image volume elements or "voxels" which are tilted with respect to the longitudinal axis of the region, and each voxel is associated with an image density value derived from the scan data.
  • a correction factor is applied to the image density values of the tilted volume elements to compensate for the tilt of the image volume elements.
  • the image density values are used to determine the mass of an object under analysis such as an explosive.
  • the determination of mass of an explosive is helpful to assess the potential threat it poses.
  • the density value for each voxel that is related to the object can be multiplied by its volume to determine the mass represented by the voxel.
  • the computed masses of all the voxels identified as being related to the target, i.e., explosive, are then summed to determine the total mass of the object. Compensating for the tilt of the voxel provides a more accurate determination of mass such that a better assessment of threat is obtained.
  • a total object mass can be computed by identifying the voxels which are associated with the object of interest , i.e., explosive, compensating for tilt of the voxels and totaling the masses for the identified voxels. Identifying related voxels can be accomplished applying the density value associated with each voxel to a density value threshold.
  • the threshold is selected based on known densities of known materials, i.e., explosives. Those values which exceed the threshold are concluded to be associated with the target material, and, therefore, their associated voxels are concluded to be related to an image of the target material. These voxels are used in the total mass computation.
  • the present invention are applied to a correction factor used to compensate of the tilt of the voxels with respect to the longitudinal axis of the region.
  • the products of the compensated volumes and related densities are then summed to determine the total mass.
  • the density thresholding can be accomplished by applying the volume elements to a multiplying window function. Values which exceed the threshold are applied to a unit multiplier of the window and those that do not exceed the threshold are applied to a zero multiplier to effectively discard them from the total mass computation.
  • the present invention is directed to a processing method and system which provide for efficient processing of the nutated image data slices generated in accordance with the nutating slice reconstruction approach of the invention.
  • This aspect of the invention provides a processing architecture which provides multiple independent processing paths for groups of image slice data instead of a more conventional pipeline processing approach in which the slices would be processed serially.
  • scan data for a region are generated by scanning the region with a radiation source and an array of detectors. To scan the region, at least the radiation source rotates about a longitudinal axis of the region through a plurality of view angles while the radiation source emits radiation toward the array of the detectors.
  • the scan data therefore comprise a plurality of sets of projection data, each set of projection data being acquired at a respective view angle.
  • each set of projection data includes a plurality of projections, e.g., fan-beam projections.
  • Each fan-beam projection in a set of projection data is used to generate an image data slice, a plurality of projections within each set of projection data being used to generate a respective plurality of image data slices.
  • each image data slice is generated from a plurality of fan-beam projections, with a single fan-beam projection being taken from each of a plurality of sets of projection data for the slice.
  • slice data for each image data slice are generated from a respective associated set of fan-beam projections.
  • Each image data slice is associated with a respective data storage element which, in one embodiment, is a memory circuit. Projections from the image data slice to be generated are stored in the data storage element. The stored projections from each data storage element are processed to generate slice data for the image data slice associated with the data storage element.
  • a processor receives the scan data from the array of detectors and generates the fan-beam projections from the sets of projection data within the scan data in accordance with the NSR approach described above. The processor then transfers the projections to the data storage elements associated with the image data slices being generated.
  • a demultiplexor circuit can be included between the processor and the data storage elements to control routing slice data projections to their associated data storage elements.
  • each image data slice to be generated is associated with a single processor which generates the projections for that slice.
  • the projections are transferred by the associated processor to an associated data storage element, e.g., memory circuit, from which the projections will be retrieved to generate the slice data for the image data slice.
  • one or more demultiplexor circuits can be placed between the plurality of processors and a plurality of data storage elements to control transfer of the projections to the data storage elements.
  • all of the processors can transfer projections to any of the data storage elements.
  • each processor can only transfer projections to a selected group of data elements.
  • processing the scan data into image data slices is accomplished much more quickly and efficiently than in the single processor pipeline approach.
  • the slice data are further processed to generate actual image data slices which will in turn be used to generate an image of the region.
  • This further processing can include filtering and/or backprojection to generate the image slices.
  • the projections generated by the processor and/or processors are typically fan-beam projections.
  • further processing can be performed on the fan-beam projections to rebin them to parallel- beam projections.
  • one of the processors can be used to perform the rebinning procedure while the others continue to be used to generate projections. The one processor can be temporarily switched to the rebinning procedure and then switched back to generating projections after rebinning is complete. This saves considerable hardware by eliminating the need for an additional processor dedicated to rebinning.
  • the CT apparatus and method of the invention provide numerous advantages over prior approaches. It provides a three-dimensional scanning approach in the form of helical cone-beam scanning, which is far less time consuming than prior approaches using linear detector arrays. It provides a reconstruction process which results in image quality comparable to three- dimensional reconstruction algorithms, but does not require three-dimensional reconstruction hardware. The much simpler two-dimensional reconstruction hardware is used. Furthermore, the approach to generating two-dimensional projection images used in the invention is much more efficient than prior approaches such as those used in prior baggage scanning systems in which a separate line scanner is used to produce the projection image as part of a pre- scanning process.
  • the present invention can provide target detection and target size and mass determination with improved accuracy over an approach which does not compensate for voxel tilt. Also, by applying the nutating slice reconstruction approach to the parallel processing architecture of the invention, images can be generated much more efficiently than if a conventional pipeline processing approach were used.
  • FIG. 1. is a schematic axial view of a typical conventional computed tomography (CT) scanner.
  • FIG. 2 is a schematic diagram which illustrates the projection angle and the detector angle of a CT scanning system.
  • FIG. 3 A illustrates the scanning path for a constant z-axis (CZA) scanning mode in a CT scanner.
  • CZA constant z-axis
  • FIG. 3B illustrates the scanning path for constant-speed-helical (CSH) scanning in a CT scanner.
  • FIG. 4 is a simplified schematic diagram which illustrates the spatial relationships among the source, detectors and scanning object in a CT scanner in accordance with the present invention.
  • FIG. 5 is a simplified schematic illustration of the projection of a tilted slice onto a two-dimensional detector array.
  • FIG. 6 is a simplified schematic illustration of the tilt and rotation angle of a tilted slice in accordance with the present invention.
  • FIG. 7 is a simplified schematic diagram of projections of a tilted slice onto a flat detector array.
  • FIG. 8 is a simplified schematic diagram of projections of a tilted slice onto a curved detector array.
  • FIG. 9 contain schematic plots of the total projected area of a tilted slice and a perpendicular slice versus view angle.
  • FIG. 10 is a simplified schematic diagram of a slice projection onto a curved detector array.
  • FIG. 11 is a simplified diagram showing slice projection lines on a two- dimensional curved array for projection angles between 0° and 240°, in increments of 20° .
  • FIG. 12 is a schematic plot which shows slice separation in the z-axis direction in accordance with the present invention.
  • FIG. 13 is a graphical illustration of the relationship between the frames of reference for an object being scanned and the nutated image data slices generated in accordance with the present invention.
  • FIG. 14 is a schematic illustration which illustrates generating a two- dimensional projection image in accordance with the present invention.
  • FIG. 15 is a schematic functional block diagram which illustrates generating and processing nutating slice data in accordance with the invention using a pipeline processing approach.
  • FIG. 16 is a schematic functional block diagram which illustrates generating and processing nutating slice data in accordance with the invention using a parallel memory processing approach with a single processor.
  • FIG. 17 is a schematic functional block diagram which illustrates generating and processing nutating slice data in accordance with the invention using a parallel memory approach with multiple parallel processors.
  • FIG. 4 is a schematic diagram which illustrates the functional operation of one embodiment of the CT scanning system 100 of the invention.
  • the system includes an x-ray source 110 which emits x-rays toward a two-dimensional x-ray detector array 112.
  • the detector array 112 is shown as a flat array having coordinates z' and q. A curved array can also be used.
  • the x-rays diverge in a cone-beam which passes through an object 116 being scanned.
  • the x-rays, attenuated by the object 116, are detected by the individual detectors 118 in the detector array 112.
  • the array 112 of detectors includes multiple rows 120 of detectors along the z'-axis and multiple columns 124 along the q-axis.
  • the cone- beam 114 therefore can be considered to consist of multiple fan beams spread along the q-axis and adjacent to each other along the z'-axis.
  • the object 116 defines a z- axis (also referred to herein as the longitudinal axis) and an orthogonal x-axis (also referred to herein as the transverse axis).
  • the x-ray source 110 and detector array 112 are secured to diametrically opposite sides of an annular shaped disk (not shown).
  • the disk is rotatably mounted within a gantry support (not shown) such that the source 110 and detector array 112 are simultaneously rotatable about the z-axis and, hence, about the object 116 being scanned.
  • the system 100 uses helical cone-beam scanning such that, as the gantry rotates about the z-axis, the gantry and object 116 are also translated relative to one another along the z-axis.
  • the gantry with source and detector array rotate through an increasing projection angle ⁇ as the gantry translates along the z-axis.
  • scan data are collected by the detector array.
  • Image data in the form of a series of image slices are then reconstructed from the projection data.
  • Each slice defines a planar configuration of image data and is generated from a predefined collection of scan data gathered as the source and detector array rotate.
  • the present invention projects a two-dimensional data slice onto the two- dimensional array of detectors such that the projection of the slice at each projection angle can be considered a one-dimensional fan-beam projection.
  • the projection onto the array falls on a group of detectors which are not necessary in a single row or column.
  • the projection will extend across several rows and columns. In the present invention these rows and columns are identified for each projection angle. A value is generated for each location at each projection angle from the projection data, in one embodiment, by interpolating the projection data.
  • a "fan beam” of detector data is generated, very much analogous to the fan beam data generated in two-dimensional fan beam scanning applications which use a linear detector array.
  • the result is a set of "fan beam” data for each projection angle.
  • these data can be applied to any suitable two- dimensional back projection algorithm to reconstruct image slices as if it were actual fan beam data.
  • the rows and columns of the detector array which receive the associated fan beam are identified before an actual scan is performed.
  • a simulation or calibration scan which simulates helical cone-beam scanning of an opaque disk, can be performed.
  • the simulated projection of the disk onto the array is recorded in the detector data.
  • the projection data is analyzed to determine which rows and columns of the array receive the projection of the disk at each projection angle. The simulation process creates a
  • each projection angle is associated with a group of detector rows and columns which should be read during subsequent scans of actual objects to generate the ID fan beam data.
  • the fan beam data at each projection angle are detected from the associated array row and columns stored in the z-interpolation table.
  • an actual opaque disk can be subjected to helical cone-beam scanning with an actual source and detector array to generate the z-interpolation table.
  • fan-beam projections are collected for each slice to be reconstructed.
  • data is collected for one half of a complete revolution of the gantry (180°) plus the angle subtended by the detector array.
  • the array subtends a 60° angle; hence, each slice is generated from data collected during 240° of gantry revolution.
  • projections are produced every 1 ° of projection angle. Therefore, in this embodiment, each slice is generated from 240 fan-beam projections.
  • the groups of projections for successive slices along the z-axis can overlap each other. For example, slices may be generated every 12° of rotation. Therefore, in the embodiment described above, 228 out of 240 projections are shared by each pair of adjacent slices.
  • the reconstructed slices in the present invention are not perpendicular to the z-axis as in conventional non-cone-beam scanning. Instead, they are tilted or nutated with respect to the z-axis, and the normal axes of successive slices precess about the z-axis.
  • Each slice defines a slice plane having a normal axis which forms an angle with the longitudinal or z-axis about which the scanning system rotates.
  • the use of a tilted slice reduces the error in the reconstructed slice data.
  • the angle of tilt can be determined using the simulation scan mentioned above and also described below in more detail.
  • the selected angle is the angle at which the projection of the opaque disk onto the array produces the least image reconstruction error.
  • FIG. 5 is a schematic diagram which illustrates acquisition of data during the simulation scan for a single projection at a single angle using a tilted reconstruction image slice represented by the titled opaque disk 132.
  • the cone beam of x-rays 114 is emitted by the source 110 and passes through the object (not shown) and illuminates the flat two-dimensional detector array 112.
  • the plane of the slice or disk 132 forms an angle ⁇ with an axis orthogonal to the z- axis. Equivalently, the normal axis to the slice plane forms the angle ⁇ with the z- axis.
  • An elliptical projection or shadow 130 of the tilted disk 132 is projected onto the detector array 112.
  • the location and shape of the projection 130 of the disk 132 changes.
  • the area of the projected ellipse changes.
  • the tilt angle ⁇ is fixed as the disk 132 translates through the detector array.
  • the spread of the ellipse (the length of its minor axis) at each projection angle is an indication of the error introduced in reconstructing the slice at that projection angle.
  • the object is to select a disk geometry that minimizes the total projected ellipse area over all of the projection angles, e.g., 240°, for the tilted slice being reconstructed.
  • the area is minimized by reconstructing a tilted slice where the normal to the slice plane is tilted by a small angle ⁇ .
  • FIG. 6 is a schematic diagram which illustrates the relationship between a tilted slice 132 and the system axes.
  • the normal 140 to the slice plane forms an angle ⁇ with the z-axis, which is referred to herein as the tilt angle or nutation angle.
  • the normal axis 140 also forms a rotation angle ⁇ with the x-axis or transverse axis of the system.
  • each slice can be reconstructed from projections whose projection angles span the range of 0° to 180° plus the array angle (60°). At one degree per projection, each slice is reconstructed from 240 projections. For any given slice, a particular slice tilt angle ⁇ and rotation angle ⁇ will yield the smallest error over all 240 projections. In one embodiment, adjacent slices are reconstructed every twelve degrees of rotation from overlapping sets of 240 projections shifted by twelve degrees. Each slice is associated with a tilt angle ⁇ and rotation angle ⁇ which minimize the reconstruction error in the slice.
  • the tilt angle ⁇ remains constant and the rotation angle ⁇ increases or decreases to define a rotation or precession of the normal axes of slices about the z-axis, as illustrated by the arrow 142 in FIG. 6.
  • the error at each tilt angle is determined by summing the total area of all disk projections over the entire 240° of data. The tilt angle yielding the minimum total error is taken as the tilt angle. In one embodiment, a tilt angle of approximately 1.45° is used.
  • FIG. 7 is a schematic diagram showing projections of the disk 132 at a tilt angle of 1.4° passing through the scan region.
  • the figure assumes a flat detector array.
  • the detector array can also be curved. In that case, the projections of the disk or slice onto the array will not be ellipses as shown in FIG. 7. They will actually be curved figures as shown in FIG. 8.
  • FIG. 8 shows the same projections as FIG. 7 with a tilt angle of 1.4°, except that the detector array 112 is curved.
  • FIG. 9 An example of the total projection area plotted as a function of view is shown in FIG. 9.
  • the dashed line shows the area for a tilt angle of 1.45° and the solid curve shows the area for no tilt angle.
  • the tilt angle is chosen as the angle which minimizes the total area, which in one embodiment is determined to be 1.45°
  • the simulation scan can also be used to identify the pixel rows and columns used for each projection at each different projection angle.
  • FIG. 10 is an example of a single tilted slice projection onto the curved detector array. All of the detectors on the array are read to identify the location of the projection 150 and, therefore, the detector rows and columns which should be read during future scans of actual objects at the particular projection angle.
  • the array includes ten rows i of 252 detectors j each.
  • the dashed line 150 indicates the spread of the curved elliptical projection on the array.
  • the solid line 152 identifies the line of detectors that are read during subsequent scans at this particular projection angle.
  • the line 152 is identified by computing the centroid of the detector values across each row. It is this solid line 152 that defines the detectors to be read during subsequent scans of an actual object. This process is completed at each projection angle for the slice to be reconstructed.
  • the simulation or calibration process associates each projection angle with a row and column value and stores them together in a "z-interpolation table. " This table is read during subsequent scans to identify the scan data used to reconstruct actual slices.
  • FIG. 11 shows a set of disk projections on a two-dimensional curved array for a slice tilted at 1.45° at view angles between 0 and 240°, spaced by 20° each. These are the array row/column lines generated for each projection angle during the calibration scan. The row/column numbers plotted for each projection angle are stored in the z-interpolation table. The array used for this plot is a standard array consisting of 24 detector rows i of 252 detectors j each. As described above, each of the curved lines is identified by computing the centroid of the projection on the array at each view angle.
  • the projection data can be obtained by helical cone- beam scanning.
  • the projection data can be corrected for offsets, gain error and non-linear effects.
  • the HCB data is applied to the z-interpolation process, which extracts the desired fan-beam data.
  • detector row and column numbers are retrieved from the z-interpolation table, and X-ray intensity values at the identified detector rows and columns are recorded as the fan-beam data.
  • the z-interpolation process can proceed as follows: At each view, the process steps through each detector j, one at a time.
  • a row number I is identified from the z-interpolation table, which is in general some real number. Where the row number i is not a whole number, interpolation can be performed on the actual data values at the appropriate row numbers to identify a value for the particular detector as described below. In one embodiment, linear interpolation is used, but other forms of interpolation can be used.
  • the interpolated data values can be treated as if they were fan beam values obtained during a conventional two- dimensional scanning procedure. They can optionally be applied to a rebinning process to produce parallel-ray data. The rebinned two-dimensional data can then be applied to a conventional one-dimensional convolution procedure. Finally, the parallel-convolved data can be applied to a conventional two-dimensional back projection algorithm. The above process is repeated for each slice in the region.
  • L( ⁇ ,q) is the line of the desired ID projection (z ' - L( ⁇ ,q)).
  • F( ⁇ ,q) may optionally be rebinned to parallel data at this stage.
  • the rebinning is the preferred method due to the computational efficiency of backprojecting parallel views rather than fan views. The rebinning procedure is discussed in detail below.
  • the cone beam data does not exist in continuous form and a method for discrete implementation is used. Specifically, the data on the line L( ⁇ ,q) must be determined by interpolating from discrete detectors.
  • the cone beam data be given by C[v,r,d], where v is the view number (in the ⁇ direction), r is the detector row number (in the z-direction), and d is the detector channel number (in the ⁇ -direction) in a given row.
  • N ⁇ is the number of half scan views
  • N d is the number of detectors per row.
  • ⁇ v ⁇ ⁇ (2)
  • z 1 (r-r)w r (3)
  • q (d-d)w d (A)
  • ⁇ ⁇ is the angle between views
  • w r is the distance between rows
  • w d is the distance between detectors in a given row
  • the desired data lies along a line which intersects the ellipse.
  • F[v,dJ be the fan beam data selected from C[v,r,d].
  • the interpolation in the r direction is referred to as the z-interpolation.
  • r '[v,d be a lookup table which gives the location of the desired point in r for a given v and d.
  • the fan data can be obtained by using linear interpolation in r. Namely,
  • the z-interpolation table can be determined by simulating projection data for the simulated tilted disk, as described above.
  • the simulated disk has thickness equal to the detector row width projected to the isocenter.
  • the attenuation coefficient is constant throughout the disk, and the photon energy is monoenergetic. In this way, a given projection ray measured through the disk is directly proportional to the thickness traversed.
  • the center of the disk is located at the isocenter and oriented with a fixed tilt angle ⁇ .
  • the disk travels in the z-direction at the specified table speed of the scanner.
  • the radius of the disk is equal to the scan radius R given by
  • ⁇ ⁇ is the angle between detectors in a given row.
  • the full detector width in the z-direction at isocenter is given by
  • s t is the table speed and T is the gantry rotation period. For example, for a pitch of one, the table moves a distance D in one rotation.
  • the simulation can use the same geometry of the scanner. Alternatively, the simulation can use more detector rows to improve the resolution in determining the z-interpolation table. See Table 1.
  • the interpolation line is determined by computing the centroid in the row direction of the resultant projection data.
  • m be the simulation row index
  • the z-interpolation table is a function of the tilt angle, the geometry of the scanner, and the pitch.
  • the pitch is fixed by the table speed, the gantry rotational speed, and detector size per Equation (11).
  • the tilt angle can be chosen by a method described below.
  • a slice is reconstructed by using a set of N ⁇ views.
  • Steps 1 through 3 above are repeated for a different set of ⁇ h views for each slice.
  • Let j be the slice number in the series of ⁇ slices, 0 ⁇ j ⁇ N j .
  • the fan data for slice j are extracted from the cone beam data as follows:
  • the plane of a tilted slice can be described by two rotations.
  • the first rotation is about the x-axis by an angle ⁇ and the second rotation is about the z-axis by an angle ⁇ .
  • the equation of the nutated plane is given by
  • the precession angle, ⁇ is related to the view angle ⁇ .
  • ⁇ the gantry angle corresponding to v OJ be denoted as ⁇ or
  • the precession angle for slice j is given by
  • ⁇ is half the fan angle as shown in FIG. 2 and defined in Equation (9).
  • a z0 is the separation of slices at isocenter given by
  • Re 30,947 which is inco ⁇ orated herein by reference.
  • the rebinning in terms of the discrete data.
  • the fan views needed to form 180 degrees of parallel views is equal to the number of fan views contained in 180 + 2 ⁇ degrees of gantry rotation. If an overscan correction is used, more fan views are needed as discussed below.
  • the rebinning procedure is the same with or without overscan. The rebinning can be done in two steps by separating the radial (q- direction) and tangential (v-direction) interpolations. The relation between fan and parallel views is given by
  • ⁇ p is the parallel view angle
  • ⁇ f is the fan view angle
  • ⁇ f is the fan detector angle.
  • v p be the parallel view index, (0 ⁇ v p ⁇ N p )
  • v / be the fan view index (0 ⁇ v f ⁇ N h ).
  • the parallel view angle is given by
  • the radial interpolation is done as follows. Let t be the location of the desired equi-spaced parallel detectors.
  • w diso is the detector channel spacing (in q) at isocenter
  • d p is the parallel detector channel number, (0 ⁇ d p ⁇ M )
  • d cp is the center parallel detector. The number of parallel detectors per view is given by
  • the parallel projection P[v p ,d p ] is obtained by interpolating the hybrid projection data in the d f ,
  • the combination of the z-interpolation and rebinning consists of interpolation of the cone beam data in all three directions, i.e., v f , d, and r.
  • the z- interpolation can be done first, or it can be inserted into the rebinning procedure.
  • parallel views should be symmetric over a range of 180 degrees. That is, a view taken at 0 degrees and a view at 180 degrees should contain the same information in the absence of motion due to symmetry.
  • Object (or patient) motion destroys this symmetry and causes a discontinuity in the projection data for views separated by 180 degrees. This discontinuity results in artifacts in the reconstructed image which lead to the development of correction schemes such as the correction scheme described in U.S. Patent No. 4,580,219, incorporated herein by reference.
  • the second method has less output views than the first method. At first it may seem advantageous to backproject less views for computational efficiency. However, in a pipelined architecture the first method may be more efficient. This is because in the second method two views separated by N p are added together. It may not be possible in a pipeline to save a view in order to add it to another view that is acquired at a later time. Both methods will produce the same final image.
  • each nutated slice used to produce images in accordance with the invention is reconstructed from projection data taken at a plurality of projection or view angles.
  • 240 total projections or views are taken at 240°, one projection or view for every degree.
  • data for successive slices are separated by 12°, resulting in an overlap between adjacent slices of 228 projections.
  • each projection taken at each view can be considered a fan-beam projection which, in one embodiment of the present invention, is rebinned to parallel-ray data before it is reconstructed into image data for the slice.
  • the present invention also makes use of this rebinned projection data to create a projection image of the region being scanned from a single angle.
  • This two-dimensional projection image is similar to what would be obtained if the region were to be scanned by the source and detector with the source and detector rotationally stationary while translated along the longitudinal axis of the region.
  • This is also similar to the image obtained by a stationary x-ray line scanner which obtains image data from only a single angle through the region being scanned.
  • the projection image can be generated from the rebinned parallel-ray data obtained from the projection data gathered during scanning which, as described above, can be performed helically as the source and detector rotate about the object and translate along the object.
  • a projection angle for the two-dimensional projection image is selected. For example, it may be desired to produce a projection image of the region from top to bottom, i.e., looking vertically into the region. In that case, the projection angle selected would be 0°. In another embodiment, it may be desirable to look at the object from the side. Accordingly, the selected projection angle would be 90°. In another situation, it may be desirable to view the region from several different angles. In that case, multiple projection angles can be selected, for example, 0°, 120° and 240°, such that the region can be viewed from evenly-spaced angles.
  • data are selected from the rebinned fan beam projections to generate the two-dimensional image.
  • a single projection or view taken from a single corresponding view angle is selected for each slice.
  • the selected view angle for a slice is the angle which corresponds to the projection angle selected for the projection image. It can be seen that for successive slices, the view used in the projection image is different. For example, as in the described embodiment of the present invention, where adjacent slices are separated by 12 views, the rebinned view data selected for adjacent slices, corresponding to the same preselected projection angle, will be offset by 12 views.
  • the view selected from the next adjacent slice would be the 18th view.
  • the selected view data are combined to generate the two-dimensional image of the region from the selected projection angle.
  • One prior approach to acquiring a projective image in CT is to scan the object with no gantry rotation while translating the object through the gantry.
  • projective images are extracted from nutated slice projections obtained while the gantry is rotated.
  • each slice be separated by a constant incremental angle.
  • corresponding view angles in adjacent slices can be regarded as being separated from each other by a constant ⁇ v views.
  • ⁇ v 12 views.
  • the first view angle in each slice is separated from the first view angle in adjacent slices by ⁇ v views; the second view angle in each slice is separated from the second view angle in adjacent slices by ⁇ v views; etc.
  • Let the first parallel projection be located at a view v 0 .
  • a parallel projection at v 0 + ⁇ v is selected.
  • This process continues for any desired length, i.e., any number of slices, or until there are no more slices.
  • the result of combining the selected views is a parallel projective image at a fixed view angle. It should be noted that the projective image is nutated since the data are selected from nutated projection data. The final projective image can be interpolated to parallel if desired.
  • N 240, as described above.
  • For each slice j there exists a view V y which contains the data corresponding to the preselected projection angle, and for the next adjacent slice, j + 1, there exists a view Vj + ⁇ v j+ j which contains the data for the slice j + 1 that corresponds to the preselected projection angle.
  • FIG. 14 pictorially illustrates generation of the two-dimensional image projection of the invention.
  • the views for the projective image are selected from data that have been rebinned to parallel geometry.
  • rebinned parallel data for each view in the image projection effectively include a series of parallel lines or samples 249 at the projection angle.
  • the selected projection angle ⁇ is selected to be 30°, that is, it is desired to produce a two-dimensional image of the scanning region 247 looking through the region at an angle of 30°.
  • each slice generated in accordance with the foregoing description there is a single projection or view, comprising a set of rebinned parallel data 249, taken from a corresponding view angle which would provide the data for the 30° view through the region.
  • the 30th view is selected since that view provides the data corresponding to the 30° projection through the region.
  • the 18th view is selected.
  • the 6th view is selected.
  • the 174th view is selected. This accounts for the fact that, instead of acquiring a full 360° of data for each slice, only 180° plus twice the fan angle, or 240°, of data are obtained.
  • the data used to generate these projections are already gathered by the initial scan, the data can be processed to produce projections from any angle. Additionally, multiple angles can be selected. This can be useful where it is desirable to view the region from different angles to identify suspect objects in the region. For example, it may be difficult to identify a prohibited item such as a hand gun using a view from only a single angle. However, where multiple projections are produced, the hand gun can be more readily identified.
  • the projection image processing can be used as a pre-screening process to identify suspect bags in a baggage scanner. The image data for the suspect baggage can then be completely reconstructed to generate a full three-dimensional image of the baggage, if required.
  • each slice defines a set of image volume elements or "voxels. " In traditional CT systems, these voxels are oriented with their axes parallel to corresponding coordinate axes in the field of view in the CT system. However, in the system of the present invention, as described above, the slices are nutated or tilted so that the volume elements are tilted with respect to the axes of the CT scanning region.
  • One application for the CT scanning system of the invention is in a commercial airport baggage scanner, as described above.
  • One capability of the baggage scanner of the invention is identification of target substances such as explosives by analyzing scan data of the substance acquired by the system.
  • One approach to identifying explosives is to compare the image density value for the substance obtained by the scanning system to known densities of known explosive materials. Densities within a predetermined tolerance of the known explosive density are concluded to be explosives. Further examination can then be performed to further analyze the item.
  • the total mass of the explosive can be computed by multiplying each density value of each voxel related to an explosive by its volume. The individual voxel masses from the voxels having densities which are identified as possibly being explosive densities are summed to determine the total mass of the explosive.
  • the voxels are tilted with respect to the scanning axis of the system. This results in slight errors when calculating the mass associated with a voxel.
  • titled voxels can be interpolated to non-tilted density values, or, a correction factor can be computed to compensate for the tilt in the voxel. Either approach provides the ability to more accurately determine the total mass of a suspect object. Detailed descriptions of these approaches follow.
  • the frames of reference of the object being scanned and the nutated CT slices reconstructed by NSR are illustrated graphically in FIG. 13.
  • the fixed frame of reference, on which the object is defined, is the yz-space, and the frame of reference for the titled slices is defined by the x'y '-axes.
  • the origin of the titled slice is at z 0 .
  • the nutation angle is ⁇ and the precession angle is ⁇ .
  • the nutation angle is amplified in this figure to emphasize the nutation and tilting of the reconstructed slices. In practice, the nutation angle can be small enough so that cos ⁇ ⁇ 1 and sin ⁇ ⁇ 0.
  • NSR a series of two-dimensional (2D) slices are reconstructed.
  • the coordinate system of the 2D slices is the x'y '-plane, where the origin of this space is along the z-axis at z 0 as shown in FIG. 13.
  • the 2D slices are nutated from the z- axis by ⁇ . Note that the nutation takes place about the origin, z 0 .
  • the precession angle of the nutation is given by ⁇ , where ⁇ is measured with respect to the x-axis.
  • the nutation is performed about a new -axis that is formed by rotating about the z- axis by ⁇ .
  • f'(x',y';z 0 ) be a slice of the continuous object function in the nutated space at z 0 .
  • the rotations are given by the matrices
  • Equation (46) says that the x'- and y '-axes map directly into the x- and y- axes, respectively. However, the z-axis is compressed or expanded depending on the x'-y' position, the precession angle, ⁇ , and the nutation angle, ⁇ . It follows that
  • the pixel size, ⁇ is 2R/N
  • Similar relationships can be written for images in the nutated space.
  • the sampled nutated space is given by F(i ', j', k'), where
  • i ', j ' are the sample indices along the x '-, and y '-z ' axes, respectively .
  • the index k' is the sample index of the tilted slices corresponding to ⁇ 0 .
  • the ranges of the indices are 0 ⁇ ' ⁇ N, 0 ⁇ j' ⁇ N, and - ⁇ ⁇ k ' ⁇ ⁇ .
  • the parameter ⁇ . • is the z-axis spacing between the nutated slices and is generally not equal to ⁇ ⁇ .
  • the collection of slices is denoted by F (i ,j, k), where i and j correspond to sampling in the imaging plane (i.e., the xy- plane) and k corresponds to sampling in the axial direction (i.e., the z-direction).
  • the in-plane pixel size is ⁇ .
  • the axial sampling distance is ⁇ z . Therefore, the volume of each voxel is ⁇ 2 xy ⁇ z .
  • the function F (i, j, k) represents the density of the object
  • the mass of the voxel located at ( , / ' , k) is ⁇ (i, j, k).
  • a procedure for determining which voxels are part of an explosive is implemented.
  • a typical method for this procedure is connected components labeling (CCL).
  • CCL components labeling
  • the output of this procedure is a binary "window" function, W (i, j, k), indicating if the voxel located at (i, j, k) is part of an explosive. Therefore,
  • the mass of the explosive, M e is given by
  • One advantage of using (64) over (61) is that the interpolation between F'(i'J', k') and F (i,j, k) is eliminated.
  • the interpolation increases partial volume artifacts that can lower the density values of thin explosives. This lowering, in turn, makes the task of determining which voxels are part of an explosive more difficult.
  • a parallel processing architecture is employed to generate and process the nutated image data slices of the invention to provide more efficient processing than would be obtained in a conventional pipeline processing system.
  • the improved efficiency realized by the parallel processing architecture results in greatly improved image generation efficiency and therefore makes the system applicable to high-scanning-throughput settings such as in the airport baggage scanner of the invention.
  • FIG. 15 contains a schematic functional block diagram of a serial pipeline approach to generation and processing of nutated slice data in accordance with the present invention.
  • the data acquisition system (DAS) 300 which includes the radiation source and array of detectors, acquires the scan data and transfers them to a data correction process 302.
  • the data correction process applies corrections to the data such as those required to compensate for air detector readings, detector temperature offsets, detector non-linearities, and general imperfections in the system.
  • the scan data are transferred to the nutating slice reconstruction data generation 304 which extracts the fan-beam projections from the sets of projection data in the scan data, as described above in detail.
  • the generated fan-beam projections can be applied to an optional rebinning process 307 to generate rebinned parallel-beam projections from the fan-beam projections.
  • the fan-beam or rebinned parallel- beam projections are transferred to a filtering process 306 which filters the projections and then to a backprojection process 308 which generates the image data for the slices.
  • the slice image data are used to generate an image 310.
  • each set of projection data from each individual view is used to generate projections for multiple adjacent slices. This is due to the overlap of slice data in successive or adjacent views.
  • each slice is generated from scan data acquired at 240 discrete views. Therefore, for each slice, at each of 240 positions around the longitudinal axis, a single fan-beam projection is extracted from the full set of projection data acquired at that position.
  • each slice is separated by only 12°of view rotation. As a result, there is considerable overlap of scan data over many slices. That is, the scan data acquired at one particular view angle are used to generate many slices.
  • each set of projection data at single view can be used in generating 20 slices.
  • each view actually contributes to 22 slices, in one embodiment.
  • the NSR process 304 illustrated in FIG. 15 actually generates projections for many slices, e.g., 22, simultaneously. That is, instead of generating a single projection for a single slice at each of the 240 views, it actually generates 22 projections at each of the 240 views. This can be a heavy processing load in a pipeline processing configuration.
  • FIG. 16 is a schematic functional block diagram which illustrates a parallel configuration in accordance with the invention which can be used to generate and process the projections used to generate the nutated slices of the invention.
  • a DAS 300 generates scan data which are corrected by a data correction process 302 before being forwarded to the NSR process 304A.
  • the NSR process can be performed by a single processor 305 which analyzes the scan data to generate the fan-beam projections needed to generate the nutated slices.
  • the processor 305 At each projection angle, the processor 305 generates a fan-beam projection for each slice to which the projection data under consideration contributes data.
  • each set of projection data will contribute to several slices, e.g., 22, and, therefore, several projections will be generated.
  • each slice being generated is associated with its own data storage element or memory 312.
  • each set of projection data may contribute to as many as 22 slices, there are 22 memories 312A-312V used to store generated projections.
  • the processor 305 At each view, the processor 305 generates a projection for each slice. The projection generated for a slice is forwarded to and stored in the memory element 312 associated with that slice. In general, where 22 slices are being generated simultaneously, 22 projections are generated from each view and are stored in 22 respective associated memories 312. This process of generating projections and storing them in preassigned memories continues until all require data are processed.
  • a single slice is complete, i.e., all of the projections for a slice have been generated and stored in its respective associated memory.
  • the projections stored in the memory element which are those required to generate the single slice, are forwarded to a mux 314 which selects the memory that is providing the slice projections.
  • the full set of projections for the slice can then be transferred to an optional rebinning process 307 which can rebin the fan-beam projections to parallel-beam projections.
  • a filtering process 306 can be performed on the data and then backprojection 308 can be performed to generate image data for the nutated slice.
  • an image 310 can be produced.
  • the process of filling the memories 312 with projections continues through all views at which scan data were acquired. Since slices are separated by 12 views in one embodiment, for every 12 views processed, one of the memories 312 becomes full with the required 240 projections for a slice. On the next view, the memory which was filled on the previous view begins being filled again with projections from another slice to be generated. Hence, where slices are separated by, for example, 12 views, generation of projections for a slice is completed every 12 views. Accordingly, every 12 views, a memory element 312 fills up. On the next view that memory element begins gather elements for a new slice. This configuration allows slice projection data to be processed very efficiently. Projections are generated for multiple slices simultaneously, but the actual slices can be rebinned, filtered and backprojected one at a time.
  • FIG. 17 is a schematic functional block diagram of another embodiment of the invention using a parallel configuration to generate and process the nutated slices of the invention.
  • the parallel memories 312A-312V are used in the same fashion as described above in connection with FIG. 16 to store fan-beam projections for individual slices as they are generated.
  • the configuration includes a multiple-processor stage 304B which includes multiple data correction stages 302A - 302H coupled respectively to multiple NSR processing stages 305 A -305H.
  • Scan data are received from the DAS 300 by a demultiplexor circuit 320, which routes the data to a selected one of the 302/305 data correction and nutating slice processing stages.
  • Each correction/nutating slice processing stage 302/305 receives data for a single view from the demux 320. It analyzes the set of projection data from the single view to generate fan-beam projections for each of the slices for which the particular view contributes projection data. The generated projections are then transferred to the memories 312 associated with the slices that use the generated projections. Again, in the example described herein, each view contributes a single projection to each of 22 slices and, therefore, the processor 305 transfers 22 projections to 22 memory elements 312A-312V for each view or set of projection data. In the embodiment shown in FIG. 17, eight nutating slice correction/processing elements 302/305 are used. It will be understood that different numbers of processing elements can be used.
  • the demux 320 cycles through the eight elements one at a time as the sets of projection data for each view are received from the DAS 300. This provides a level of parallelism to the scan data processing and therefore greatly increases the speed at which the processing can be performed. This is very helpful in settings such as the baggage scanner in which high scanning throughput is required.
  • all of the nutating slice processing elements can transmit projections to any of the memory elements 312.
  • each processor 305 can only communicate with a portion of the memory elements 312. This approach can be used to simplify communication between the processors 305 and the memories 312 and also to eliminate contention for the memories 312.
  • a memory element 312 becomes full of projections for a slice when it contains 240 projections. The full set of projections is transferred via mux 314 to the optional rebinning process 307. After the fan-beam projections are rebinned to parallel-beam projections, they are filtered 306 and backprojected 308 into image slices. The slices can then be used to generate an image 310.
  • the rebinning process 307 can be implemented on one of the processing elements 305.
  • one of the processors 305 is commanded to perform the rebinning.
  • a processor is commanded to perform rebinning, when that processor completes its present task of generating projections of a particular view, instead of processing the next view, it is temporarily interrupted so that it can perform the required rebinning function.
  • the processor rejoins the other processors in the projection data processing cycle.
  • any of the processors can be commanded to perform rebinning at any time. This approach to sharing a processor eliminates hardware complexity in the system by reducing the number of processors and associated circuitry in the system.

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  • Pulmonology (AREA)
  • Apparatus For Radiation Diagnosis (AREA)
  • Image Processing (AREA)

Abstract

Un système de tomographie assistée par ordinateur (CT) à coupe de nutation génère au moyen d'un balayage de faisceau conique hélicoïdal (114) des données de projection tridimensionnelles, et reconstitue une série de coupes d'images planes (132) présentant des angles d'inclinaison égaux (υ) et des angles de rotation variables par rapport à l'axe longitudinal de l'objet balayé, provoquant ainsi une nutation et une précession des normales autour de l'axe longitudinal (Z). On utilise une reconstitution bidimensionnelle traditionnelle étant donné que les données de projection (130) des coupes inclinées (132) représentent des données de faisceau plat unidimensionnelles, les images bidimensionnelles pouvant être créées selon des angles de projection fixes. La nutation ou l'inclinaison des voxels peuvent en outre être compensées, et un traitement parallèle utilisé.
EP19980948103 1997-10-10 1998-09-04 Detection de cible par tomographie assistee par ordinateur Withdrawn EP1021128A1 (fr)

Applications Claiming Priority (7)

Application Number Priority Date Filing Date Title
US08/948,697 US5887047A (en) 1997-04-09 1997-10-10 Parallel processing architecture for computed tomography scanning system using non-parallel slices
US948491 1997-10-10
US08/948,491 US5909477A (en) 1997-04-09 1997-10-10 Computed tomography scanning target detection using non-parallel slices
US948697 1997-10-10
US948492 1997-10-10
US08/948,492 US5881122A (en) 1997-04-09 1997-10-10 Computed tomography scanning apparatus and method for generating parallel projections using non-parallel slice data
PCT/US1998/018561 WO1999018854A1 (fr) 1997-10-10 1998-09-04 Detection de cible par tomographie assistee par ordinateur

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EP1021128A1 true EP1021128A1 (fr) 2000-07-26

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EP (1) EP1021128A1 (fr)
JP (1) JP3585835B2 (fr)
CN (1) CN1336811A (fr)
AU (1) AU9474398A (fr)
WO (1) WO1999018854A1 (fr)

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JP4887132B2 (ja) * 2006-12-21 2012-02-29 ジーイー・メディカル・システムズ・グローバル・テクノロジー・カンパニー・エルエルシー Ｘ線ｃｔ装置
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WO1999018854A1 (fr) 1999-04-22
AU9474398A (en) 1999-05-03
CN1336811A (zh) 2002-02-20
JP2001519192A (ja) 2001-10-23

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