|Veröffentlichungsdatum||16. Dez. 2008|
|Eingetragen||3. Juli 2003|
|Prioritätsdatum||15. Okt. 1999|
|Auch veröffentlicht unter||DE60014001D1, DE60014001T2, EP1092392A2, EP1092392A3, EP1092392B1, US6256368|
|Veröffentlichungsnummer||10613791, 613791, US RE40607 E1, US RE40607E1, US-E1-RE40607, USRE40607 E1, USRE40607E1|
|Erfinder||Jiang Hsieh, Mark Edward Woodford|
|Ursprünglich Bevollmächtigter||General Electric Company|
|Zitat exportieren||BiBTeX, EndNote, RefMan|
|Patentzitate (15), Referenziert von (2), Klassifizierungen (13), Juristische Ereignisse (3)|
|Externe Links: USPTO, USPTO-Zuordnung, Espacenet|
This invention relates generally to methods and apparatus for cardiac CT imaging, and more particularly to methods and apparatus that minimize an impact of heart motion in collecting calcification data from coronary images.
In at least one known computed tomography (CT) imaging system configuration, an x-ray source projects a fan-shaped beam which is collimated to lie within an X-Y plane of a Cartesian coordinate system and generally referred to as the “imaging plane”. The x-ray beam passes through the object being imaged, such as a patient. The beam, after being attenuated by the object, impinges upon an array of radiation detectors. The intensity of the attenuated beam radiation received at the detector array is dependent upon the attenuation of the x-ray beam by the object. Each detector element of the array produces a separate electrical signal that is a measurement of the beam attenuation at the detector location. The attenuation measurements from all the detectors are acquired separately to produce a transmission profile.
In known third generation CT systems, the x-ray source and the detector array are rotated with a gantry within the imaging plane and around the object to be imaged so that the angle at which the x-ray beam interests the object constantly changes. A group of x-ray attenuation measurements, i.e., projection data, from the detector array at one gantry angle is referred to as a “view”. A “scan” of the object comprises a set of views made at different gantry angles, or view angles, during one revolution of the x-ray source and detector. In an axial scan, the projection data is processed to construct an image that corresponds to a two-dimensional slice taken through the object. One method for reconstructing an image from a set of projection data is referred to in the art as the filtered back projection technique. This process converts the attenuation measurements from a scan into integers called “CT numbers” or “Hounsfield units”, which are used to control the brightness of a corresponding pixel on a cathode ray tube display.
A main objective of cardiac CT applications is to perform calcification scoring, a diagnostic procedure in which an amount of calcification present in a patient's heart is estimated. At least one known CT imaging system requires about 0.5 s to complete data acquisition for an image. Although this speed is satisfactory for general imaging purposes, it is not fast enough to avoid motion-induced image artifacts in cardiac CT imaging, in which a typical cardiac cycle is about 1.0 s long. These artifacts present major problems for cardiac calcification scoring.
At least one other known CT imaging system reduces motion-induced image artifacts by acquiring data rapidly enough to effectively freeze cardiac motion. This imaging system employs a scanning electron beam to generate a moving source of x-rays rather than an x-ray source and detector on a rotating gantry. However, CT imaging systems employing scanning electron beams are quite expensive and are not available at many hospitals.
It would therefore be desirable to provide methods and apparatus that overcome motion-induced artifacts produced in images acquired by CT imaging systems having relatively slow scanning and detection systems such as rotating gantries. It would also be desirable to provide cardiac calcification scoring methods and apparatus utilizing such CT imaging systems. It would further be desirable to provide methods and apparatus that can readily identify and score calcification from the small incremental x-ray attenuation produced by small amounts of calcification.
There is therefore provided, in one embodiment of the present invention, a method for producing CT images of a patient's heart suitable for calcification scoring, in which the heart has a cardiac cycle. The method includes steps of acquiring data representative of a first scout-scanned CT image of physical locations of the patient's body including at least a portion of the patient's heart at phases φ1(L) of the cardiac cycle, acquiring data representative of a second scout-scanned CT image of the physical locations of the patient's body including at least a portion of the patient's heart at phases φ2(L) of the cardiac cycle different from φ1(L) at physical positions L of interest, and determining a difference image from the acquired data representative of the first scout-scanned CT image and the acquired data representative of the second scout-scanned CT image data. It is not necessary that φ1(L) and φ2(L) be constant as a function of position L.
The above described embodiment overcomes motion-induced image artifacts by making calcification signals more readily observable as a change between images. Moreover, even small amounts of calcification are readily identifiable and qualifiable, because much larger variations in x-ray attenuations that would otherwise hide calcification deposits are canceled out.
Rotation of gantry 12 and the operation of x-ray source 14 are governed by a control mechanism 26 of CT system 10. Control mechanism 26 includes an x-ray controller 28 that provides power and timing signals to x-ray source 14 and a gantry motor controller 30 that controls the rotational speed and position of gantry 12. A data acquisition system (DAS) 32 in control mechanism 26 samples analog data from detector elements 20 and converts the data to digital signals for subsequent processing. An image reconstructor 34 receives sampled and digitized x-ray data from DAS 32 and performs high speed image reconstruction. The reconstructed image is applied as an input to a computer 36 which stores the image in a mass storage device 38.
Computer 36 also receives commands and scanning parameter from an operator via console 40 that has a keyboard. An associated cathode ray tube display 42 allows the operator to observe the reconstructed image and other data from computer 36. The operator supplied commands and parameters are used by computer 36 to provide control signals and information to DAS 32, x-ray controller 28 and gantry motor controller 30. In addition, computer 36 operates a table motor controller 44 which controls a motorized table 46 to position patient 22 in gantry 12. Particular, table 46 moves portions of patient 22 through gantry opening 48 along a z-axis. In some of the embodiments described below, cardiac cycles are measured utilizing EKG machine 50.
An amount of calcification present in the cardiac system of patient 22 is reliably estimated from scout images taken with CT imaging system 10 in one embodiment of the present invention. Patient 22 is instructed to hold his or her breath while images of the heart of patient 22 are scanned by CT imaging system 10 in a scout imaging mode of operation. Because patient 22 is holding his or her breath, the only moving object within the scan field of view is the heart of patient 22. Data for two scout scans are obtained, and a difference between the data for the two images is used to remove non-moving body structure and highlight calcification, as explained below.
In one embodiment of the invention and referring to
Data representing a second scout image (not shown) is also acquired. The second scout scan image is acquired in a manner that ensures that corresponding columns of the second scout scan are taken at times during which heart 58 is in a different phase of first scout image 52. In this manner, data representative of a first and a second scout-scanner CT image of physical locations of the body of patient 22 are obtained. Data for each physical location is obtained at different phases of the cardiac cycle in the two images.
For example, referring to
In one embodiment, scout scans are manually started. For example, phases of EKG signal 64 from EKG machine 50 are manually monitored to determine trigger times to begin each scout-scanned data acquisition. In another embodiment, scans are started automatically. For example, computer 36 of CT imaging system 10 is configured to receive and monitor EKG signal 64 or an equivalent to determine trigger times.
During scanning, patient 22 holds his or her breath and remains as still as possible to minimize differences between the first and the second scout images other than those related to heart movement. It is reasonable to request patients to hold their breath during the scanning and feasible for patients to comply with such requests due to the brevity of the procedure.
It will be observed that data for each scout image, for example, image 52, is a composite representing different phases of heart 58. Each physical location L represented by data of the first scout image is acquired at a phase φ1(L) of the cardiac cycle. For the second scout image, data for location L is acquired at a phase φ2(L), where φ1(L)≠φ2(L). Because of the amount of time taken by table 46 to travel from one end of each scout scan to the other, neither φ1 nor φ2 are constant across each scout image. However, their difference at any location L is constant, or nearly so. The present invention advantageously uses this difference to highlight cardiac calcification.
Columns of intensity (or equivalently, attenuation) data is obtained by detector array 18 while table 46 moves to obtain a scout scan. Each column, for example column 54 shown in
In one embodiment, image processing techniques are used by computer 36 to further isolate, identify, and score calcification peaks such as peak 74. For example, intensities of small groups of pixels 76 of a difference image 78 shown in part in
In one embodiment, a difference image is enhanced by image processing to enhance the appearance of calcification 74 utilizing, for example, contrast enhancement algorithms. Differencing or other image processing procedures needed for contrast enhancement are implemented, for example, in hardware, software, or firmware of image reconstructor 34 or computer 36, or both. In one embodiment, computer 36 is programmed both to display a difference image on CRT 42 and to automatically recognize and score calcification 74 by analysis of the difference image.
In one embodiment, scans of the two scout images are triggered by EKG signal 64 from EKG machine 50. The EKG signal is supplied to computer 36, which controls scanning and acquisition of image data in CT imaging system 10. Computer 36 ensures that the two scout images taken are images of the same region of the body of patient 22 by controlling movement of table 46. Computer 36 also ensures that the heart is in a different cardiac phase by staring the scans at different points in a cardiac cycle.
In an embodiment in which CT imaging system 10 is a multi-slice imaging system having more than one row of detector elements 20, similar procedures for movement of table 46 are followed. However, a plurality of difference images are obtained, one for each row of detector 18.
In another embodiment, multiple detector rows of a detector 16 in a multi-slice CT imaging system 10 are used in a single pass to generate a difference image. Computer 36 adjusts a rate of movement of table 46 during acquisition of data so that a small time lag occurs between acquisition of image data of the same body portions patient 22 by different rows of detector array 18. Computer 36 selects an amount of time lag in accordance with a heart rate of patient 22 determined, for example, from EKG signal 64. The amount of time lag is selected to ensure that image data is acquired by different rows of detector 18 during different portions of a cardiac cycle. In this manner, image data acquired from two different rows of a multi-slice detector 18 obtained during a single pass of a scout scan is used to obtain two suitable scout images. A difference image for scoring is computed from those portions of the two scout images that include at least a portion of heart 58 and that represent the same physical locations of the body of patient 22. Portions of each image acquired by the two rows of detector 18 that do not overlap are simply ignored.
In another embodiment utilizing a multi-slice CT imaging system 10 having more than two rows of detectors, additional information for estimating background noise in obtained. For example, three or more rows of detectors obtain three or more scout images, including two for computing a difference image, and noise estimation information including at least a third scout image. Background noise in the difference image is estimated and reduced utilizing the noise estimation information and standard signal processing techniques.
From the preceding description of various embodiments of the present invention, it is evident that the problem of motion-induced artifacts in CT imaging systems is overcome, especially for calcification scoring purposes. Moreover, by reducing or eliminating non-moving body parts in a difference image, scoring of calcification is readily accomplished, even though only small incremental x-ray attenuation is produced by calcification.
Although particular embodiments of the invention have been described and illustrated in detail, it is to be clearly understood that the same is intended by way of illustration and example only and is not to be taken by way of limitation. Accordingly, the spirit and scope of the invention are to be limited only by the terms of the appended claims and legal equivalents.
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|US-Klassifikation||378/98.12, 378/95, 378/8|
|Internationale Klassifikation||H05G1/62, G01N23/083, A61B6/03|
|Unternehmensklassifikation||A61B6/503, A61B6/032, A61B6/488, A61B6/541|
|Europäische Klassifikation||A61B6/48N, A61B6/03B, A61B6/50F|
|17. Dez. 2008||FPAY||Fee payment|
Year of fee payment: 8
|11. Febr. 2013||REMI||Maintenance fee reminder mailed|
|3. Juli 2013||LAPS||Lapse for failure to pay maintenance fees|