Computed tomography scanner with large gantry bore

• US 7,324,623 B2
• Filed: 07/12/2004
• Issued: 01/29/2008
• Est. Priority Date: 07/15/2003
• Status: Active Grant

• Current Assignee: Koninklijke Philips Electronics N.V. (Koninklijke Philips N.V.)
• Original Assignee: Koninklijke Philips Electronics N.V. (Koninklijke Philips N.V.)
• Inventors: Heuscher, Dominic J.
• Primary Examiner(s): KAO, CHIH CHENG G
• Application Number:
  US10/564,715
• Publication Number:
  US 20060159220A1
• Time in Patent Office: 1,296 Days
• Field of Search: 378/4, 378/9, 378/19, 378/16, 382/131
• US Class Current: 378/9
• CPC Class Codes: A61B 6/027 characterised by the use of a particular data acquisition trajectory, e.g. helical or spiral
• CPC Class Codes: A61B 6/032 Transmission computed tomography [CT]
• CPC Class Codes: A61B 6/4014 arranged in multiple source-detector units
• CPC Class Codes: A61B 6/4291 the detector being combined with a grid or grating
• CPC Class Codes: A61B 6/482 involving multiple energy imaging
• CPC Class Codes: G01N 23/04 and forming images of the material

Abstract

A computed tomography scanner includes a rotating gantry (20) defining an examination region (16). A first radiation source (22) is disposed on the rotating gantry (20) and emits first radiation (32) into the examination region (16). A second radiation source (24) is disposed on the rotating gantry (20) and emits second radiation (36) into the examination region (16). The second radiation source (24) is angularly spaced around the gantry from the first radiation source (22). A first radiation detector (30, 30′) receives the first radiation (32). A center of the first radiation detector (30, 30′) is angularly spaced around the gantry from the first radiation source (22) by less than 180°. A second radiation detector (34) receives the second radiation (36). A center of the second radiation detector (34) is angularly spaced around the gantry from the second radiation source (24) by less than 180°.

Claims

1. A computed tomography imaging system including:

a rotating gantry that rotates about an examination region along a longitudinal axis;

a first radiation source disposed on the rotating gantry and arranged to emit first radiation into the examination region;

a second radiation source disposed on the rotating gantry and arranged to emit second radiation into the examination region, the second radiation source being angularly spaced around the gantry from the first radiation source;

a first asymmetrically adjustable collimator that is asymmetrically adjustable in a direction generally perpendicular to the longitudinal axis to position a first outer x-ray projection of the first radiation relative to a second outer x-ray projection of the first radiation;

a second asymmetrically adjustable collimator that is asymmetrically adjustable in a direction generally perpendicular to the longitudinal axis to position a first outer x-ray projection of the second radiation relative to a second outer x-ray projection of the second radiation;

a first radiation detector arranged to receive the first radiation, a center of the first radiation detector being angularly spaced around the gantry from the first radiation source by less than 180°

;

a second radiation detector arranged to receive the second radiation, a center of the second radiation detector being angularly spaced around the gantry from the second radiation source by less than 180°

; and

a reconstruction processor that reconstructs projection data acquired during gantry rotation by the first and second radiation detectors into one or more image representations;

wherein the first asymmetrically adjustable collimator has a fixed collimation edge that defines the second outer x-ray projection of the first radiation and an adjustable collimation edge that defines the first outer x-ray projection of the first radiation,

the second asymmetrically adjustable collimator has a fixed collimation edge that defines the second outer x-ray projection of the second radiation and an adjustable collimation edge that defines the first outer x-ray projection of the second radiation, and

each of the adjustable collimation edges moves between a first position at which the first and second radiation is symmetrical about the rotational center and at least one other position at which the first and second radiation is asymmetrical about the rotational center.

2. The computed tomography imaging system as set forth in claim 1, wherein the first radiation detector includes:

a high resolution portion having detector elements of a first size; and

a low resolution portion having detector elements of a second size, the second size being larger than the first size.

3. The computed tomography imaging system as set forth in claim 2, wherein the second radiation detector includes:

a high resolution portion having detector elements of the first size; and

a low resolution portion having detector elements of the second size;

wherein the high resolution portions of the first and second radiation detectors are arranged angularly between the low resolution portions of the first and second radiation detectors on the rotating gantry.

4. The computed tomography imaging system as set forth in claim 3, further including:

a non-stationary filter that smooths a transition between projection data acquired by the low resolution portions of the first and second radiation detectors and projection data acquired by the high resolution portions of the first and second radiation detectors.

5. The computed tomography imaging system as set forth in claim 2, wherein:

the angular spacing of the first radiation detector from the first radiation source by less than 180°

defines symmetric and asymmetric beam components of the first radiation, the symmetric beam component being centered on a rotational center of the rotating gantry;

the high resolution portion of the first radiation detector is arranged to receive the symmetric beam component; and

the low resolution portion of the first radiation detector is arranged to receive the asymmetric beam component.

6. The computed tomography imaging system as set forth in claim 1, wherein the first and second radiation detectors each span greater than 90°

around the gantry.

7. The computed tomography imaging system as set forth in claim 1, wherein the second radiation source is angularly spaced from the first radiation source by 90°

.

8. The computed tomography imaging system as set forth in claim 1, wherein the second radiation source is angularly spaced from the first radiation source by at least 90°

, and each of the first and second radiation detectors spans greater than 90°

around the gantry.

9. The computed tomography imaging system as set forth in claim 1, wherein the first and second radiation sources lie in a plane parallel to a plane of gantry rotation.

10. The computed tomography imaging system as set forth in claim 1, wherein the first and second radiation sources are relatively offset in an axial direction by one-half of an axial spacing of detector elements of the first and second radiation detectors.

11. The computed tomography imaging system as set forth in claim 1, wherein the first and second radiation sources are relatively offset in an axial direction by less than an axial dimension of a conebeam at a scan-center.

12. The computed tomography imaging system as set forth in claim 1, wherein the first and second radiation sources are conebeam radiation sources, and the first and second radiation detectors are two-dimensional arrays, the computed tomography imaging system further including:

a support element for supporting an associated imaging subject in the examination region, the support element being linearly movable in an axial direction, simultaneous gantry rotation and axial motion of the support element effecting a helical orbit of the first and second radiation sources relative to the associated imaging subject during acquisition of the projection data.

13. The computed tomography imaging system as set forth in claim 12, wherein the first and second radiation sources are relatively offset in the axial direction by an amount such that the second radiation source follows the first radiation source along the helical orbit.

14. The computed tomography imaging system as set forth in claim 1, wherein:

the first radiation detector includes a first anti-scatter grid focused on the first radiation source; and

the second radiation detector includes a second anti-scatter grid focused on the second radiation source.

15. The computed tomography imaging system as set forth in claim 1, wherein:

a first radiation energy of the first radiation is different from a second radiation energy of the second radiation; and

the reconstruction processor reconstructs projection data acquired by the first and second radiation detectors into one or more combined image representations having contributions from projection data acquired by the first and second radiation detectors.

16. The computed tomography imaging system as set forth in claim 1, further including:

a radiation source control that alternates between generating radiation by the first radiation source and generating radiation by the second radiation source such that the first and second radiation sources are not simultaneously generating radiation.

17. The computed tomography imaging system as set forth in claim 1, wherein the reconstruction processor includes:

a backprojector; and

a weighting processor that applies a weighting function to projection data prior to backprojecting, the weighting processor applying a first weighting function to projection data for reconstruction of voxels in a central region of the examination region, the weighting processor applying a second weighting function for reconstruction of voxels outside the central region, the second weighting function being dependent upon a distance of the voxel outside the central region from the center of rotation.

18. A computed tomography imaging system including:

a rotating gantry defining an examination region, the examination region including a central region that contains a center of rotation of the rotating gantry and a surrounding region that surrounds the central region, the rotating gantry further defining a gantry plane of gantry rotation and an axial direction;

a first radiation source disposed on the rotating gantry, the first radiation source producing first radiation directed into the examination region;

a first radiation detector array arranged to receive the first radiation after the first radiation passes through the examination region, the first detector array including;

a high resolution portion with detector elements of a first size that receive first radiation that passes through the central region, and

a low resolution portion with detector elements of a second size that receive first radiation that passes through the surrounding region but not the central region, wherein the second size is larger than the first size;

a second radiation source disposed on the rotating gantry, the second radiation source being positioned at an angular offset on the rotating gantry relative to the first radiation source, the second radiation source producing second radiation directed into the examination region;

a second radiation detector array arranged to receive the second radiation after the second radiation passes through the examination region, the second detector array including;

a high resolution portion with detector elements of a third size that receive second radiation that passes through the central region, and

a low resolution portion with detector elements of a fourth size that receive second radiation that passes through the surrounding region but not the central region, wherein the fourth size is larger than the third size,

wherein the high resolution portions of the first and second radiation detector arrays are arranged on the rotating gantry between the low resolution portions of the first and second radiation detector arrays;

wherein the first and second radiation detector arrays together define a single unitary radiation detector array, the single unitary radiation detector array including;

a central high resolution portion defined b the high resolution portions of the first and second radiation detector arrays;

a first outer low resolution portion defined by the low resolution portion of the first radiation detector array; and

a second outer low resolution portion defined b the low resolution portion of the second radiation detector array, wherein the central high resolution portion is arranged between the first and second outer low resolution portions; and

a reconstruction processor that reconstructs projection data acquired during gantry rotation by the first and second radiation detector arrays into an image representation.

19. The computed tomography imaging system as set forth in claim 18, further including:

a first asymmetrically adjustable collimator that is asymmetrically adjusted to move a first outer x-ray projection of the first radiation relative to a second outer x-ray projection of the first radiation; and

a second asymmetrically adjustable collimator that is asymmetrically adjusted to move a first outer x-ray projection of the second radiation relative to a second outer x-ray projection of the second radiation.

20. The computed tomography imaging system as set forth in claim 19, wherein the first asymmetrically adjustable collimator has a fixed collimation edge that defines the second outer x-ray projection of the first radiation and an adjustable collimation edge that defines the first outer x-ray projection of the first radiation, and

the second asymmetrically adjustable collimator has a fixed collimation edge that defines the second outer x-ray projection of the second radiation and an adjustable collimation edge that defines the first outer x-ray projection of the second radiation.

21. The computed tomography imaging system as set forth in claim 18, wherein the reconstruction processor includes:

a backprojector; and

a weighting processor that weights the projection data prior to backprojecting, the weighting processor applying;

90°

weighting windows for backprojecting voxels in the central region of the examination region,

180°

weighting windows for backprojecting voxels in the surrounding region of the examination region, and

asymmetric weighting windows for backprojecting voxels in a transition region intermediate between the central region and the surrounding region.

22. The computed tomography imaging system as set forth in claim 18, wherein the low resolution portion of each detector includes two low resolution sub-portions of equal size, the high resolution portion of each detector being disposed between the two low resolution sub-portions such that the first and second radiation detector arrays are symmetric detector arrays.

23. The computed tomography imaging system as set forth in claim 18, wherein each detector element of the low resolution portion of each detector includes a plurality of detector elements of the first size that are electrically interconnected.

24. A computed tomography imaging method including:

passing first radiation through an examination region, the examination region including a central region and a surrounding region;

measuring central projections, corresponding to rays of first radiation that intersect the central region, using a first high-resolution detector array that has a first spacing of detector elements;

measuring surrounding projections, corresponding to rays of first radiation that intersect the surrounding region without intersecting the central region, using a first low-resolution detector array that has a second spacing of detector elements, the second spacing being larger than the first spacing;

passing second radiation through the examination region;

measuring central projections, corresponding to rays of second radiation that intersect the central region, using a second high-resolution detector array that has the first spacing of detector elements;

measuring surrounding projections, corresponding to rays of second radiation that intersect the surrounding region without intersecting the central region, using a second low-resolution detector array that has the second spacing of detector elements; and

reconstructing the central projections and the surrounding projections corresponding to the first radiation and the second radiation to generate a reconstructed image representation, wherein the reconstructing includes;

combining 90°

contiguous angular segments of the central projections corresponding to the first radiation and the second radiation during reconstructing of voxels within the central region; and

combining 180°

contiguous angular segments of the central and surrounding projections corresponding to the first radiation and the second radiation during reconstructing of voxels in the surrounding region outside a transition radius.

25. The method as set forth in claim 24, wherein the first radiation is substantially monochromatic at a first energy and the second radiation is substantially monochromatic at a second energy that is different from the first energy, and the reconstructing includes:

reconstructing the central projections measured using the first high-resolution detector array and the surrounding projections measured using the first low-resolution detector array to generate a first reconstructed image representation; and

reconstructing the central projections measured using the second high-resolution detector array and the surrounding projections measured using the second low-resolution detector array to generate a second reconstructed image representation.

26. The method as set forth in claim 24, wherein the passing of the first radiation and the passing of the second radiation do not overlap temporally.