Patent Application
20090304158
The invention relates generally to diagnostic imaging and, more particularly, to a modular multispot x-ray source for use in an imaging system and a method of making same.
Traditional x-ray imaging systems include an x-ray source and a detector array. X-rays are generated by the x-ray source, passed through and attenuated by an object, and are detected by the detector array. Hereinafter, the terms “subject” and “object” shall include anything capable of being imaged. The intensity of the attenuated beam radiation received at the detector array is typically dependent upon the attenuation of the x-ray beam by the object. Each detector element of the detector array produces a separate electrical signal indicative of the attenuated beam received by each detector element. The electrical signals are transmitted to a data processing system for analysis which ultimately produces an image.
Generally, as in a CT application, the x-ray source and the detector array are mounted on a gantry and rotated about an imaging plane and around the object. X-ray sources typically include x-ray tubes, which emit the x-ray beam at a focal point. X-ray detectors typically include a collimator for collimating x-ray beams received at the detector, a scintillator adjacent the collimator for converting x-rays to light energy, and photodiodes for receiving the light energy from the adjacent scintillator and producing electrical signals therefrom. The X-ray detectors may also include a direct conversion device for discriminating the energy content of the x-ray beam. The outputs of the detector array are then transmitted to the data processing system for image reconstruction. Electrical signals generated by the detector array are conditioned to reconstruct an x-ray image of the object.
In CT imaging systems, the gantry rotates at various speeds in order to create a 360° image of the object. The gantry contains an x-ray source having an electron source or cathode assembly that generates electrons that are accelerated across a vacuum gap to a target or anode assembly via a high voltage potential. In releasing the electrons, a filament contained within the electron source is heated to incandescence by passing an electric current therethrough. The electrons are accelerated by the high voltage potential and impinge upon a target surface of the target at a focal spot. Upon impingement, the electrons are rapidly decelerated and, in the process, x-rays are generated therefrom.
The process of deceleration typically results in heating of the focal spot to very high temperatures. Thus, X-ray tubes include a rotating target or anode structure for the purpose of distributing heat generated at the focal spot. The target is typically rotated by an induction motor having a cylindrical rotor built into a cantilevered axle that supports a disc-shaped target and an iron stator structure with copper windings that surrounds an elongated neck of the x-ray tube. The rotor of the rotating target is driven by the stator. Because of the high temperatures generated when the electron beam strikes the target, the target is typically rotated at high rotational speed.
Newer generation x-ray tubes have increasing demands for providing higher peak power, thus generally higher average power as well. Higher peak power, though, would result in higher peak temperatures occurring in the target, particularly at the “track” or the point of impact on the target, unless the target design is altered. Because x-ray tubes are typically designed having peak temperatures at limits imposed by material capabilities and high voltage considerations, higher peak power typically calls for a redesign of the target. For a rotating target, the redesign may include higher rotation speed, larger track radius, or novel x-ray production means. These designs will often pose risks of reduced life and reliability. For stationary target sources, the redesign options are limited to material improvements or novel approaches to backscattered electron energy management.
Furthermore, newer generation CT systems have increased gantry speed requirements to better enable, for instance, cardiac imaging. Thus, systems have been designed having applications wherein the gantry is spun at or below 0.5 seconds rotational speed. Such applications may include yet faster gantry rotation, thereby increasing the g-load demands to, for instance, 0.2 second rotation, which represents a g-load well in excess of what can be withstood in current CT systems.
Accordingly, to counter the need for high g-load capability x-ray sources, multispot systems have been designed having stationary imaging components therein. For instance, scanning electron beam (e-beam) x-ray sources include an electron gun positioned at a gantry center that emits an e-beam that is magnetically deflected toward a target. In such a system, the target typically forms a continuous ring surrounding a patient, and the e-beam is rapidly deflected to circumferential locations on the target and around the patient. The e-beam may be deflected in the z-direction as well. As such, multispot imaging may be performed very rapidly using stationary components. However, not only are such systems expensive, they may be prone to performance degradation as well. For instance, the continuous target may have thermal distortion that can degrade image quality through excessive focal spot motion.
Furthermore, other known systems having stationary components include a thin transmission-style target for x-ray generation. However, such a continuous target is likewise prone to thermal loading and distortion effects resulting, as well, in degraded image quality through excessive focal spot motion.
Therefore, it would be desirable to design a cost-effective modular multispot x-ray source having robust g-load capability and improved thermal loading capability.
The invention is a directed to an apparatus and method of manufacturing a cost-effective modular multispot x-ray source having robust g-load capability and improved thermal loading capability.
According to one aspect of the invention, a modular x-ray source for an imaging system includes an electron source mounting plate, two or more electron sources each mounted on and electrically coupled to the electron source mounting plate, and a target block positioned proximately to the two or more electron sources. The source includes two or more targets mounted on and electrically coupled to the target block, each target positioned opposite a respective one of the two or more electron sources to receive a respective beam of electrons therefrom.
In accordance with another aspect of the invention, a method of manufacturing a modular x-ray source includes forming an array of electron sources that are configured to each emit a beam of electrons, forming an array of targets, each spaced one from the other in substantially the same pattern as the array of electron sources, and positioning the array of targets proximately to the array of electron sources such that each electron source in the array of electron sources emits electrons to a respective target within the array of targets.
Yet another aspect of the invention includes an x-ray imaging system that includes a rotatable gantry, a detector mounted to the rotatable gantry, and a modular x-ray source mounted to the rotatable gantry. The modular x-ray source includes at least two electron sources mounted on a first plate, at least two targets mounted on a second plate, and two high voltage insulators positioned between the first plate and the second plate. Each electron source is positioned to emit electrons to a respective target.
Various other features and advantages of the invention will be made apparent from the following detailed description and the drawings.
The drawings illustrate one preferred embodiment presently contemplated for carrying out the invention.
In the drawings:
The operating environment of the invention is described with respect to a sixty-four-slice computed tomography (CT) system. However, it will be appreciated by those skilled in the art that the invention is equally applicable for use with other multi-slice configurations. The invention will be described with respect to a “third generation” CT scanner, but is equally applicable with other CT systems.
Referring to
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 an x-ray source 14 and a gantry motor controller 30 that controls the rotational speed and position of gantry 12. An image reconstructor 34 receives sampled and digitized x-ray data from DAS 32 and performs high-speed 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 parameters from an operator via console 40 that has some form of operator interface, such as a keyboard, mouse, voice activated controller, or any other suitable input apparatus. An associated 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 controller 44 to position a motorized table 46 and hence patient 22 and gantry 12. Particularly, table 46 moves patients 22 through a gantry opening 48 of
The x-ray source 14 may include a modular design according to an embodiment of the invention. In this embodiment, referring to
The electron sources 110 are configured as sub-modules three of which are illustrated 114, 115, 117, and each of which includes, in the illustrated embodiment, four electron sources 110. Each electron source 110 is positioned opposite a respective target 112. The electron source sub-modules 114, 115, 117 are mounted on the electron source mounting plate 102 via electron source support blocks 116. The electron source sub-modules 114, 115, 117 and their respective electron source support blocks 116 may be mounted on additional spacers 118, 119 such as illustrated for electron source sub-modules 114, 115, such that target-electron source spacing may be controlled independently for each electron source sub-module. As illustrated, the spacers 118, 119 are designed to position each electron source 110 within each electron source sub-module 114, 115, 117 at a proper spacing with respect to its respective target 112. Thus, a 4×3 array of 12 target-electron source pairs are illustrated in the module 100.
One skilled in the art will recognize that the module 100 need not be limited to three sub-modules 114, 115, 117, nor does the number of electron sources 110 need to be limited to four within each sub-module 114. As such, a module 100 may include more or less than the 12 pairs illustrated in
The targets 112 are positioned within the target block 104 such that electrons are emitted substantially orthogonal therefrom and received from each respective electron source 110 on a focal spot surface at an angle of between 0° and 90°. In a preferred embodiment the angle is between 10° and 40°. Each electron source 112 includes tungsten, molybdenum, and/or alloys thereof including other materials, for generation of x-rays, as is commonly understood within the art. Alternatively, each electron source 112 may include field emitters. The target block 104, with its plurality of targets 112, further includes a target cover 120, positioned on the target block 104 and having a plurality of holes or passageways 122 therein. The passageways 122 are positioned to allow passage of electrons from each electron source 110 to its respective target 112, while limiting the flow of backscattered electrons and ions away from the target to the tube frame and electron source, respectively.
Module 100 is positioned within a vacuum environment in, for instance, a CT gantry. A high voltage, such as a monopolar operation having up to 140 kV or more, is applied between the electron sources 110 and the targets 112 via the electron source plate 102 and the target block 104. In this embodiment, the 140 kV voltage difference is applied by grounding the electron source plate 102 and applying +140 kV to the target block 104. However, one skilled in the art will recognize that the voltage differential may be applied in other fashions, such as by splitting the applied kV between the target block 104 and the electron source plate 102 (i.e. a bipolar operation having +70 kV to the target block 104 and −70 kV to the electron source plate 102) or by grounding the target block 104 while applying a −140 kV bias to the electron source plate 102. The split-potential embodiment may include an additional set of insulators between the target or electron source block and the vacuum chamber and attendant changes in the electrical feedthroughs from the high voltage power supply. In one embodiment, the total applied voltage differential is 450 kV or more for, for instance, a baggage scanner in a security application.
In one embodiment, coolant (such as water, dielectric oil, or glycol, as examples) is flowed through a plurality of coolant lines 124 to remove heat generated at the targets 112. Such coolant lines may be connected via a manifold that may feed several modules, and the coolant lines may be connected to the manifold via, for instance, a vacuum-compatible connector. Accordingly, the coolant lines 124 may further serve as a means to apply a bias voltage to the module 100. Thus, as an example, in such an embodiment the electron source plate 102 may be grounded and the target block 104 may be biased to +140 kV via the cooling lines 124.
Filaments (not shown) within each electron source 110 are caused to emit beams of electrons 128 toward respective targets 112. The beams of electrons 128 emit from the electron source 110 and are accelerated toward and impinge upon the targets 112 while passing through passageways 122. As such, x-rays 126 are generated and are emitted toward an imaging object, such as the object 22 of
The module 100 is thus a single or stand-alone unit that may be fabricated with a vacuum chamber and inserted into, for example, a CT system such as the CT system 10 of
One skilled in the art will recognize that the each module 100 may house its own vacuum region. In such an embodiment, a plurality of modules 100 may be positioned within a gantry, having the advantage of enabling replacement of individual modules without having to access the vacuum region 202 as discussed above.
As discussed with respect to
Furthermore, because of the compact and stand-alone nature of the module 100, the module 100 may be structurally designed to have g-load capability in a system having 0.35 second rotation and faster. Accordingly, the multi-spot source 200 illustrated in
Referring now to
A technical contribution for the disclosed method and apparatus is that it provides for a computer implemented diagnostic imaging system having a modular multispot x-ray source for use in an imaging system and a method of making same.
According to one embodiment of the invention a modular x-ray source for an imaging system includes an electron source mounting plate, two or more electron sources each mounted on and electrically coupled to the electron source mounting plate, and a target block positioned proximately to the two or more electron sources. The source includes two or more targets mounted on and electrically coupled to the target block, each target positioned opposite a respective one of the two or more electron sources to receive a respective beam of electrons therefrom.
In accordance with another embodiment of the invention a method of manufacturing a modular x-ray source includes forming an array of electron sources that are configured to each emit a beam of electrons, forming an array of targets, each spaced one from the other in substantially the same pattern as the array of electron sources, and positioning the array of targets proximately to the array of electron sources such that each electron source in the array of electron sources emits electrons to a respective target within the array of targets.
Yet another embodiment of the invention includes an x-ray imaging system that includes a rotatable gantry, a detector mounted to the rotatable gantry, and a modular x-ray source mounted to the rotatable gantry. The modular x-ray source includes at least two electron sources mounted on a first plate, at least two targets mounted on a second plate, and two high voltage insulators positioned between the first plate and the second plate. Each electron source is positioned to emit electrons to a respective target.
The invention has been described in terms of the preferred embodiment, and it is recognized that equivalents, alternatives, and modifications, aside from those expressly stated, are possible and within the scope of the appending claims.
