A tetrahedron beam computed tomography system including an x ray source array that sequentially emits a plurality of x ray beams at different positions along a scanning direction and a collimator that intercepts the plurality of x-ray beams so that a plurality of fan-shaped x-ray beams emanate from the collimator towards an object. The system includes a first detector receiving a first set of fan-shaped x ray beams after they pass through the object, the first detector generating a first imaging signal for each of the received first set of fan-shaped x-ray beams and a second detector receiving a second set of fan-shaped x ray beams after they pass through the object, the second detector generating a second imaging signal for each of the received second set of fan-shaped x-ray beams. Each detector and source pair form a tetrahedral volume. In other embodiments, the system may also have more than two detectors arrays and/or more than one source array. Each pair of source array and detector array forms a tetrahedral volume. Using multiple detector arrays and source arrays can increase field of view, reduce the length of detector and source arrays so that the imaging system is more compact and mobile.
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25. A method of forming an image of an object, the method comprising:
having an x-ray source array, first detector and second detector rotate about an axis of rotation relative to an object;
sequentially emitting a plurality of x ray beams from said x-ray source array at different positions along a scanning direction;
intercepting said plurality of x-ray beams so that a plurality of fan-shaped x-ray beams emanate towards said object;
having a first set of fan-shaped x ray beams after they pass through said object received by said first detector, said first detector generating a first imaging signal for each of said received first set of fan-shaped x-ray beams;
having a second set of fan-shaped x ray beams after they pass through said object received by said second detector, said second detector generating a second imaging signal for each of said received second set of fan-shaped x-ray beams;
receiving 1) said first imaging signals for each of said first set of received fan-shaped x-ray beams and 2) said second imaging signals for each of said second set of received fan-shaped x-ray beams, wherein rotation of said x-ray source array, said first detector and said second detector about said axis of rotation results in multiple imaging signals being reconstructed to generate a three-dimensional tetrahedron beam computed tomography image therefrom; and
displaying said three-dimensional tetrahedron beam computed tomography image.
1. A tetrahedron beam computed tomography system comprising:
an x-ray source array that sequentially emits a plurality of x-ray beams at different positions along a scanning direction;
a collimator that intercepts said plurality of x-ray beams so that a plurality of fan-shaped x-ray beams emanate from said collimator towards an object;
a first detector receiving a first set of fan-shaped x-ray beams after they pass through said object, said first detector generating a first imaging signal for each of said received first set of fan-shaped x-ray beams;
a second detector receiving a second set of fan-shaped x-ray beams after they pass through said object, said second detector generating a second imaging signal for each of said received second set of fan-shaped x-ray beams;
a computer connected to said first detector and said second detector so as to receive 1) said first imaging signals for each of said first set of received fan-shaped x-ray beams and 2) said second imaging signals for each of said second set of received fan-shaped x-ray beams, wherein said x-ray source array, said first detector and said second detector rotate about a rotation axis so as to rotate about said object so that multiple imaging signals are reconstructed by said computer to generate a three-dimensional tetrahedron beam computed tomography image therefrom; and
a display connected to said computer and displaying said three-dimensional tetrahedron beam computed tomography image.
41. A tetrahedron beam computed tomography system comprising:
a first x-ray source array that sequentially emits a first plurality of x-ray beams at different positions along a first scanning direction;
a first collimator that intercepts said first plurality of x-ray beams so that fan-shaped x-ray beams emanate from said first collimator towards an object;
a second x-ray source array that sequentially emits a second plurality of x-ray beams at different positions along a second scanning direction;
a second collimator that intercepts said second plurality of x-ray beams so that fan-shaped x-ray beams emanate from said second collimator towards said object;
a first detector receiving one or both of 1) a first plurality of fan-shaped x-ray beams from said first x-ray source array and 2) a first plurality of fan-shaped x-ray beams from said second x-ray source array after they pass through said object, said first detector generating a first imaging signal for each of said received one or both of said first plurality of fan-shaped x-ray beams from said first x-ray source array and said first plurality of fan-shaped x-ray beams from said second x-ray source array;
a second detector receiving one or both of 1) a second plurality of fan-shaped x-ray beams from said first x-ray source array and 2) a second plurality of fan-shaped x-ray beams from said second x-ray source array after they pass through said object, said second detector generating a second imaging signal for each of said received one or both of said second plurality of fan-shaped x-ray beams from said first x-ray source array and said second plurality of fan-shaped x-ray beams from said second x-ray source array;
a computer connected to said first detector and said second detector so as to receive 1) said first imaging signals for each of said first plurality of fan-shaped x-ray beams received by said first detector and 2) said second imaging signals for each of said second plurality of fan-shaped x-ray beams received by said second detector, wherein said first x-ray source array, said second x-ray source array, said first detector and said second detector rotate about a rotation axis so as to rotate about said object so that multiple imaging signals are reconstructed by said computer to generate a three-dimensional tetrahedron beam computed tomography image therefrom; and
a display connected to said computer and displaying said three-dimensional tetrahedron beam computed tomography image.
55. A method of forming an image of an object, the method comprising:
having a first x-ray source array, a second x-ray source array, a first detector and a second detector rotate about an axis of rotation relative to an object;
sequentially emitting a first plurality of x-ray beams from said first x-ray source array at different positions along a first scanning direction;
intercepting said first plurality of x-ray beams so that fan-shaped x-ray beams emanate towards said object;
sequentially emitting a second plurality of x-ray beams from said second x-ray source array at different positions along a second scanning direction;
intercepting said second plurality of x-ray beams so that fan-shaped x-ray beams emanate towards said object;
having one or both of 1) a first plurality of fan-shaped x-ray beams from said first x-ray source array and after they pass through said object and 2) a first plurality of fan-shaped x-ray beams from said second x-ray source array and after they pass through said object that are received by said first detector, wherein said first detector generates a first imaging signal for each of said received first plurality of fan-shaped x-ray beams from said first x-ray source array and said received first plurality of fan-shaped x-ray beams from said second x-ray source array;
having one or both of 1) a second plurality of fan-shaped x-ray beams from said first x-ray source and after they pass through said object and 2) a second plurality of fan-shaped x-ray beams from said second x-ray source and after they pass through said object that are received by said second detector, wherein said second detector generates a second imaging signal for each of said received second plurality of fan-shaped x-ray beams from said first x-ray source and said received second plurality of fan-shaped x-ray beams from said second x-ray source;
receiving 1) said first imaging signals for each of said first plurality of fan-shaped x-ray beams from said first x-ray source and for each of said first plurality of fan-shaped x-ray beams from said second x-ray source and 2) said second imaging signals for each of said second plurality of fan-shaped x-ray beams from said first x-ray source and for each of said second plurality of fan-shaped x-ray beams from said second x-ray source, wherein rotation of said first x-ray source array, said second x-ray source array, said first detector and said second detector about said axis of rotation results in multiple imaging signals being reconstructed to generate a three-dimensional tetrahedron beam computed tomography image therefrom; and
displaying said three-dimensional tetrahedron beam computed tomography image.
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The present application is a continuation-in-part application of U.S. patent application Ser. No. 12/803,480, filed on Jun. 29, 2010 now U.S. Pat. No. 8,611,490, which is a continuation application of U.S. patent application Ser. No. 11/786,781, filed on Apr. 12, 2007, now U.S. Pat. No. 7,760,849, which claims, under 35 U.S.C. §119(e), the benefit of priority of the filing date of Apr. 14, 2006, of U.S. Provisional Patent Application Ser. No. 60/792,207, filed on the aforementioned date, the entire contents of each of the above mentioned patent and patent applications are incorporated herein by reference.
1. Field of the Invention
The present invention relates generally to computed tomography (CT) and, more particularly, to a volumetric computed tomography (VCT) system.
2. Discussion of the Related Art
Computed tomography (CT) provides a transverse image of an object. Conventional fan beam CT uses a point x-ray source and a linear detector array. The detector array may have one or more detector rows. With a single rotation, one or more image slices can be reconstructed using computer algorithms.
In order to increase imaging speed, CT detector row number has been increased to many hundreds so that more image slices are acquired in each rotation. A wider detector array covers a larger field of view. Hence, a volumetric image can be reconstructed with a single gantry rotation. Such CT systems are often called volumetric CT (VCT) systems. VCT systems can use a two-dimensional detector, such as a flat panel imager. VCT systems that include a flat panel imager are commonly used in image guided radiotherapy and intervention as shown in U.S. Pat. No. 6,842,502, the entire contents of which are incorporated herein by reference. The patent describes an embodiment of a cone-beam computed tomography imaging system that includes a kilovoltage x-ray tube and a flat panel imager having an array of amorphous silicon detector. As a patient lies upon a treatment table, the x-ray tube and flat panel image rotate about the patient in unison so as to take a plurality of images as described previously.
There are several disadvantages when using CBCT. For example, the flat panel detector may include a scintillation screen and a charge-coupled device photodiode array. The scintillation screen converts x-ray photons into visible light photons which are then detected by a photodiode array. The performance of such flat panel detectors, in the aspect of signal-to-noise ratio, detection efficiency and sampling speed, is inferior to discrete x-ray detectors that are used in a diagnostic helical computed tomography scanner. High noise level and low detection efficiency cause poor low contrast differentiation and noisier images. A further reduction in image quality may be caused by suboptimal performance of a flat panel imager. Approximate reconstruction artifacts exist when cone angle is large.
Another disadvantage of CBCT is that when x-ray beams pass through the object 28, x-ray photons are either absorbed or scattered. Since the x-ray detector is so wide, the scattered photons are likely to be detected by the two-dimensional detector 22. Scattered photons will add up on the images, and hence attenuation information cannot be accurately measured. Scatter causes artifacts in the images. CBCT images hence have low image quality than those from fan beam CT. Besides artifacts, scatter contamination also increases noise in the images. In order to compensate noise, stronger x-ray beams have to be used. Hence, x-ray exposure of CBCT imaging is also higher than fan beam CTs. Another problem with such a VCT system is the large cost of a flat panel detector.
Current techniques for scatter correction or rejection include calculating the scatter and then subtracting the scatter from the signal. However, the length of time the scatter calculation requires can be as long as hours or days using the Monte Carlo method. Furthermore, the noise from the scatter remains after the scatter profile has been subtracted from the signal, such that the signal-to-noise ratio decreases.
In another technique, the scatter is measured and then subtracted from the signal. This technique, however, subjects the patient to additional radiation exposure and prolonged scanning time and requires an additional scan to measure the scatter profile. Further, the noise from the scatter remains, which sacrifices the signal-to-noise ratio.
In yet another technique, a grid is positioned in front of the detector and behind the patient to block some scatter. However, the grid also partially blocks the primary x-ray beams, resulting in additional radiation exposure to the patient. Other techniques use an air gap by increasing the distance from the detector to the patient, which reduces the scatter that is collected by the detector. Because of mechanical limitations, however, the distance from the detector to the patient can be increased only a finite amount.
Other systems addressing the scatter problem are known. For example, a VCT system with a two-dimensional x-ray source array and a point or small detector is disclosed in U.S. Pat. No. 7,072,436, the entire contents of which are incorporated herein by reference. This approach is also called inverse geometry CT since the detector and source geometry is reversed. Compared to regular geometry VCT, the scatter component in inverse geometry VCT is very low due to the small detector. However, in practice it is difficult to make a large two-dimensional x-ray source array that can provide sufficient field of view. The two-dimensional x-ray source array is also cumbersome to be used in mobile CT scanners.
Another VCT geometry uses a linear array of x-ray sources, and a two-dimensional area detector as described in U.S. Pat. No. 7,072,436, the entire contents of which are incorporated herein by reference. Each x-ray source generates a fan beam perpendicular to the rotation axis. This system is able to reject scatter photons and perform exact image reconstruction. It also does not have beam divergence problem in the axial direction as cone beam CT.
Note that the use of multiple fan beams in computed tomography as described in U.S. Pat. No. 6,229,870 (“the '870 patent”), the entire contents of which are incorporated herein by reference, does not require expensive area detector. It also uses a linear array of x-ray sources, and the x-ray beam from each source is collimated to its own detector array. The fan beams are also perpendicular to the rotation axis. The gap between the detector arrays can be filled in by moving the imaging subject during gantry rotation. Multiple rotations are needed for generating an image and so the system described in the '870 patent is not a true VCT system.
Tetrahedron beam computed tomography (TBCT) is another VCT system that can reconstruct a three-dimensional volume in a single gantry rotation and is described in U.S. Pat. No. 7,760,849 and U.S. patent application Ser. No. 12/803,480, the entire contents of each of which is incorporated herein by reference. TBCT employs a linear detector array and linear source array which are orthogonal to each other. The linear detector array and linear source array form a tetrahedral volume instead of a cone volume of traditional CBCT. The beams from each individual source of the source array are collimated to fan beams so that scatter component is very low. TBCT does not require a very wide detector so costs are significantly reduced. In addition, a linear array of x-ray sources is relatively easier to make when compared with a two-dimensional source array. The approximate image reconstruction artifact due to cone angle can be eliminated or reduced by using iterative image reconstruction algorithms.
Similar to that of CBCT systems, the beams of TBCT are diverged (converged). In order to achieve certain field of view (FOV) at central axis, the linear source array and detector must be almost twice as long along their respective axes as the desired FOV along those axes. Moreover because of the divergence in axial (z) direction, the volume that received radiation is larger than the volume that can be reconstructed. A mobile CT scanner requires compact design so that it can be easily mounted on C-arm gantries.
Accordingly, it is an object of the present invention to reduce scatter generated in a volumetric computed tomography system.
Another object of the present invention is to provide for a compact volumetric computed tomography system.
Another object of the present invention is to reduce beam divergence in a transverse slice.
Another object of the present invention is to reduce the lengths of detector arrays.
One aspect of the present invention regards a tetrahedron beam computed tomography system including an x-ray source array that sequentially emits a plurality of x ray beams at different positions along a scanning direction and a collimator that intercepts the plurality of x-ray beams so that a plurality of fan-shaped x-ray beams emanate from the collimator towards an object. The system includes a first detector receiving a first set of fan-shaped x ray beams after they pass through the object, the first detector generating a first imaging signal for each of the received first set of fan-shaped x-ray beams and a second detector receiving a second set of fan-shaped x ray beams after they pass through the object, the second detector generating a second imaging signal for each of the received second set of fan-shaped x-ray beams. The system including a computer connected to the first detector and the second detector so as to receive 1) the first imaging signals for each of the first set of received fan-shaped x-ray beams and 2) the second imaging signals for each of the second set of received fan-shaped x-ray beams, wherein the x-ray source array, the first detector and the second detector rotate about a rotation axis so as to rotation about the object so that multiple imaging signals are reconstructed by the computer to generate a three-dimensional tetrahedron beam computed tomography image therefrom. The system further includes a display connected to the computer and displaying the three-dimensional tetrahedron beam computed tomography image.
A second aspect of the present invention regards a method of forming an image of an object, the method including having an x-ray source array, first detector and second detector rotate about an axis of rotation relative to an object and sequentially emitting a plurality of x ray beams from the x-ray source array at different positions along a scanning direction and intercepting the plurality of x-ray beams so that a plurality of fan-shaped x-ray beams emanate towards the object. The method further includes having a first set of fan-shaped x ray beams after they pass through the object received by the first detector, the first detector generating a first imaging signal for each of the received first set of fan-shaped x-ray beams and having a second set of fan-shaped x ray beams after they pass through the object received by the second detector, the second detector generating a second imaging signal for each of the received second set of fan-shaped x-ray beams. The method includes receiving 1) the first imaging signals for each of the first set of received fan-shaped x-ray beams and 2) the second imaging signals for each of the second set of received fan-shaped x-ray beams, wherein rotation of the x-ray source array, the first detector and the second detector rotate about the axis of rotation results in multiple imaging signals being reconstructed to generate a three-dimensional tetrahedron beam computed tomography image therefrom. The method further including displaying the three-dimensional tetrahedron beam computed tomography image.
A third aspect of the present invention regards a tetrahedron beam computed tomography system that includes a first x ray source array that sequentially emits a first plurality of x ray beams at different positions along a first scanning direction and a first collimator that intercepts the first plurality of x-ray beams so that fan-shaped x-ray beams emanate from the first collimator towards an object. The system further includes a second x ray source array that sequentially emits a second plurality of x ray beams at different positions along a second scanning direction and a second collimator that intercepts the second plurality of x-ray beams so that fan-shaped x-ray beams emanate from the second collimator towards the object. The system includes a first detector receiving one or both of 1) a first plurality of fan-shaped x ray beams from the first x-ray source array and 2) a first plurality of fan-shaped x-ray beams from the second x-ray source array after they pass through the object, the first detector generating a first imaging signal for each of the received one or both of the first plurality of fan-shaped x-ray beams from the first x-ray source array and the first plurality of fan-shaped x-ray beams from the second x-ray source array. The system also includes a second detector receiving one or both of 1) a second plurality of fan-shaped x ray beams from the first x-ray source array and 2) a second plurality of fan-shaped x-ray beams from the second x-ray source array after they pass through the object, the second detector generating a second imaging signal for each of the received one or both of the second plurality of fan-shaped x-ray beams from the first x-ray source array and the second plurality of fan-shaped x-ray beams from the second x-ray source array. The system further includes a computer connected to the first detector and the second detector so as to receive 1) the first imaging signals for each of the first plurality of fan-shaped x-ray beams received by the first detector and 2) the second imaging signals for each of the second plurality of fan-shaped x-ray beams received by the second detector, wherein the first x-ray source array, the second x-ray source array, the first detector and the second detector rotate about a rotation axis so as to rotation about the object so that multiple imaging signals are reconstructed by the computer to generate a three-dimensional tetrahedron beam computed tomography image therefrom. The system including a display connected to the computer and displaying said three-dimensional tetrahedron beam computed tomography image.
A fourth aspect of the present invention regards a method of forming an image of an object, the method including having a first x ray source array, a second x-ray source array, a first detector and a second detector rotate about an axis of rotation relative to an object. The method including 1) sequentially emitting a first plurality of x ray beams from the first x-ray source array at different positions along a first scanning direction and intercepting the first plurality of x-ray beams and 2) sequentially emitting a second plurality of x ray beams from the second x-ray source array at different positions along a second scanning direction and intercepting the second plurality of x-ray beams so that a plurality of fan-shaped x-ray beams emanate towards the object. The method including having the first detector receive one or both of 1) a first plurality of fan-shaped x-ray beams from the first x-ray source array and after they pass through the object and 2) a first plurality of fan-shaped x-ray beams from the second x-ray source array and after they pass through the object, wherein the first detector generates a first imaging signal for each of the received first plurality of fan-shaped x-ray beams from the first x-ray source array and the received first plurality of fan-shaped x-ray beams from the second x-ray source array. The method including having the second detector receive one or both of 1) a second plurality of fan-shaped x-ray beams from the first x-ray source array and after they pass through the object and 2) a second plurality of fan-shaped x-ray beams from the second x-ray source array and after they pass through the object, wherein the second detector generates a second imaging signal for each of the received second plurality of fan-shaped x-ray beams from the first x-ray source array and the received second plurality of fan-shaped x-ray beams received from the second x-ray source array. The method including receiving 1) the first imaging signals for each of the first plurality of fan-shaped x-rays from the first x-ray source array and for each of the first plurality of fan-shaped x-ray beams from the second x-ray source array and 2) the second imaging signals for each of the second plurality of fan-shaped x-ray beams from the first x-ray source array and for each of the second plurality of fan-shaped x-ray beams from the second x-ray source array, wherein rotation of the first x-ray source array, the second x-ray source array, the first detector and the second detector about the axis of rotation results in multiple imaging signals being reconstructed to generate a three-dimensional tetrahedron beam computed tomography image therefrom. The method including displaying the three-dimensional tetrahedron beam computed tomography image.
One or more aspects of the present invention provide the advantage of providing a compact volumetric CT system capable of rejecting the majority of scatter photons.
One or more aspects of the present invention provide the advantage of reducing or eliminating beam divergence so that the field of view can be increased.
One or more aspects of the present invention provide the advantage of reducing the lengths of source array.
One or more aspects of the present invention provide the advantage of reducing the lengths of detector arrays.
Additional objects, advantages and features of the present invention will become apparent from the following description and the appended claims when taken in conjunction with the accompanying drawings.
Referring now to
The tetrahedron beam computed tomography system 200 includes an x-ray source array 202 and a multi-row imager/detector 204 having a curved shape mounted on a gantry 206. In particular, x-ray source array 202 is preferably a linear array of x-ray source and the multi-row detector is preferably a discrete scintillator/photodiode detector array. The detector array can be constructed from photodiode/scintillator array modules with data acquisition units, which are well known in the art.
As shown in
As shown in
In operation, electrons are generated from the cathode 211 by the potential Vg applied between the gate electrode 213 and the cathode 211. The electrons are accelerated by potential Va, and focused into a small focus spot by potential Vf and focusing electrodes 216. X-ray photons are generated via the bremsstrahlung effect when electrons strike on the molybdenum or tungsten anode target 214 and have an energy of about 80-130 keV when imaging a human. The focusing electrodes 216 direct the electrons to different portions of the anode target 214 that represent focus spots that generate individual x-ray beams. Note that in another embodiment, an x-ray source array 202 can be formed by scanning a single electron beam emitted from a single cathode.
As shown in
As described in U.S. Pat. No. 7,760,849, x-ray sources are sequentially switched on and off at a rate of approximately a few hundred Hz during a scan. As shown in
The embodiments described above can be implemented in various cone (wide) beam computed tomography systems, including on-board cone-beam computed tomography radiotherapy units, multi-row detector helical computed tomography systems, multi-row detector axial computed tomography systems, and C-arm flat panel cone-beam computed tomography systems, as well as other conventional diagnostic computed tomography systems. The applications of tetrahedron beam computed tomography can be employed in other forms of image guided interventions, such as image-guided surgery/biopsy with C-arm cone-beam computed tomography. The scatter rejection mechanism of tetrahedron beam computed tomography is also applicable to multi-row helical scanners and digital tomosynthesis.
A tetrahedron beam computed tomography system 600 that employs the components described previously with respect to
The source array 202 and detector array 204, 230 are orthogonal to each other. Both source array and detector array can be straight or curved. Each individual source 602 generates an x-ray beam which is collimated to a fan-shaped beam 604 by a multi-slot collimator 222 (not shown). The array of sources 202 generates fan beams at different angles which are received by the same detector 204, 230. Similar to cone-beam computed tomography, a volumetric image can be reconstructed by tetrahedron beam computed tomography with a single rotation. But different from cone-beam computed tomography, the detector array 204, 230 of tetrahedron beam computed tomography receives much less scatter photons due to the fan beam geometry. Consequently, tetrahedron beam computed tomography image quality and imaging dose are significantly improved.
Now referring to
Similarly three detector arrays can further reduce or eliminate the beam divergence.
Note that in the systems 700 and 800 of
As described above, the systems 700 and 800 operate by having the source and detector arrays rotate about the axis 606 and acquiring and processing image data in a manner similar to that described in U.S. Pat. No. 7,760,849. Reconstruction of the image data can be done by using a CT reconstruction algorithm or a digital tomosynthesis algorithm in a well known manner The systems 700 and 800 can achieve rotation of the x-ray sources and x-ray detectors by having them mounted on a rotating drum 210 of gantry 206 of
In an alternative embodiment, multiple source arrays 202a and 202b can be used in a tetrahedron beam computed tomography system 900 as shown in
As shown in
One advantage of TBCT system 900 is increased field of view. For example, in order to achieve the same field of view, the length of linear source array and detector array can be reduced by half. Another advantage of system 900 is that only the volume that can be reconstructed will be irradiated. With shorter sources and detectors, the TBCT system can be much more compact and suitable for use as mobile CT scanners. The system 900 also produces diagnostic quality images due to scatter rejection and the use of high quality detectors.
Note that in the system 900 of
Note in the system 800 and 900, the beam from each source is unnecessary to be collimated to all detectors. They can be collimated to one or two detector arrays. With an increase in the field of view in the z-direction, the number of detector arrays may surpass three.
Note that in each of the tetrahedron beam computed tomography systems illustrated in
With the use of multiple source arrays in system 900, the length of the source arrays and detector arrays may be similar. In this case, it does not matter which one of the detector and source is parallel to the rotation axis. Hence the positions of source arrays and detector arrays shown in
As described above, the system 900 operates by having the source and detector arrays rotate about the axis 606 and acquiring and processing image data in a well known manner. Reconstruction of the image data can be done by using a CT reconstruction algorithm or a digital tomosynthesis algorithm, wherein the latter has a lower image quality and is used when smaller angles of rotation of the sources and detectors are involved. Such rotation can be accomplished by having the x-ray sources and x-ray detectors mounted on a rotating drum 210 of gantry 206 of the radiation treatment machine of
The systems 700, 800 and 900 can have full rotation with the gantry or partial rotation. The rotation can be axial or helical depending on the image reconstruction algorithms. The data acquired by the system can be used for 3D CT image reconstruction or digital tomosynthesis image reconstruction.
The foregoing discussion discloses and describes merely exemplary embodiments of the present invention. One skilled in the art will readily recognize from such discussion, and from the accompanying drawings and claims, that various changes, modifications and variations can be made therein without departing from the spirit and scope of the invention as defined in the following claims. For example, the number of source array can be more than two. Each of the detectors does not have to receive x-ray fan beams from all sources.
Zhang, Tiezhi, Yan, Di, Kim, Joshua, Xu, Xiaochao, Martinez, Alvaro
| Patent | Priority | Assignee | Title |
| Patent | Priority | Assignee | Title |
| 3778614, | |||
| 3780291, | |||
| 4132895, | Aug 28 1976 | Thorn EMI Patents Limited | Radiography |
| 4145613, | Oct 25 1977 | CGR Medical Corporation | Motorized X-ray tube assembly |
| 4304999, | Jan 02 1979 | Technicare Corporation | Eccentric source collimator assembly for rotating source CT scanner |
| 4315157, | May 01 1980 | UAB RESEARCH FOUNDATION, THE, NON-PROFIT CORP | Multiple beam computed tomography (CT) scanner |
| 4380818, | Jun 23 1980 | Siemens Aktiengesellschaft | X-Ray diagnostic system comprising a radiography unit with an X-ray tube which emits a fan-shaped radiation beam |
| 4389569, | Dec 14 1979 | SHIMADZU CORPORATION A CORP OF JAPAN | Emission computed tomograph |
| 4405745, | Sep 24 1982 | PHILIPS PETROLEUM COMPANY, A CORP OF DEL | Polymer stabilization |
| 4414682, | Nov 17 1980 | UNITED STATES TRUST COMPANY | Penetrating radiant energy imaging system with multiple resolution |
| 4534051, | Dec 27 1982 | John K., Grady | Masked scanning X-ray apparatus |
| 4547892, | Apr 01 1977 | PICKER INTERNATIONAL, INC | Cardiac imaging with CT scanner |
| 4712226, | Sep 13 1985 | Siemens Aktiengesellschaft | Stereoscopic x-ray tube |
| 4920552, | Mar 24 1988 | U S PHILIPS CORPORATION, 100 EAST 42ND STREET, NY, NY, 10017, A CORP OF DE | X-ray apparatus comprising an adjustable slit-shaped collimator |
| 5039867, | Aug 24 1987 | Mitsubishi Denki Kabushiki Kaisha | Therapeutic apparatus |
| 5125012, | Jul 18 1990 | Siemens Aktiengesellschaft | Computer tomography apparatus |
| 5157707, | Feb 20 1989 | AO Medical Products AB | Method and a cassette holder for performing X-ray examination |
| 5214686, | Dec 13 1991 | WAKE FOREST UNIVERSITY HEALTH SCIENCES | Three-dimensional panoramic dental radiography method and apparatus which avoids the subject's spine |
| 5335255, | Mar 24 1992 | Varian Medical Systems, Inc | X-ray scanner with a source emitting plurality of fan beams |
| 5379333, | Nov 19 1993 | General Electric Company | Variable dose application by modulation of x-ray tube current during CT scanning |
| 5394452, | Mar 19 1992 | VENTURE INVESTORS EARLY STAGE FUND III LIMITD PARTNERSHIP; ADVANTAGE CAPITAL WISCONSIN PARTNERS I LIMITED PARTNERSHIP; AVALON TECHNOLOGY, LLC A MICHIGAN LIMITED LIABILITY COMPANY | Verification system for radiation therapy |
| 5411026, | Oct 08 1993 | Best Medical International, Inc | Method and apparatus for lesion position verification |
| 5485494, | Aug 03 1994 | General Electric Company | Modulation of X-ray tube current during CT scanning |
| 5521957, | Mar 15 1994 | X-ray imaging system | |
| 5533082, | Jan 28 1992 | Computer tomograph | |
| 5602892, | Mar 21 1996 | EC ENGINEERING CONSULTANTS LLC | Method for optimization of radiation therapy planning |
| 5625661, | Apr 30 1994 | Shimadzu Corporation | X-ray CT apparatus |
| 5657364, | Dec 14 1995 | General Electric Company | Methods and apparatus for detecting beam motion in computed tomography imaging systems |
| 5661773, | Mar 19 1992 | VENTURE INVESTORS EARLY STAGE FUND III LIMITD PARTNERSHIP; ADVANTAGE CAPITAL WISCONSIN PARTNERS I LIMITED PARTNERSHIP; AVALON TECHNOLOGY, LLC A MICHIGAN LIMITED LIABILITY COMPANY | Interface for radiation therapy machine |
| 5663995, | Jun 06 1996 | General Electric Company | Systems and methods for reconstructing an image in a CT system performing a cone beam helical scan |
| 5675625, | Jun 17 1994 | LAP GmbH Laser Applikationen | Apparatus for positioning and marking a patient at a diagnostic apparatus |
| 5699805, | Jun 20 1996 | Mayo Foundation for Medical Education and Research | Longitudinal multiplane ultrasound transducer underfluid catheter system |
| 5719914, | Nov 13 1995 | GE Medical Systems Global Technology Company, LLC | Method for correcting spherical aberration of the electron beam in a scanning electron beam computed tomography system |
| 5724400, | Jun 09 1993 | VENTURE INVESTORS EARLY STAGE FUND III LIMITD PARTNERSHIP; ADVANTAGE CAPITAL WISCONSIN PARTNERS I LIMITED PARTNERSHIP; AVALON TECHNOLOGY, LLC A MICHIGAN LIMITED LIABILITY COMPANY | Radiation therapy system with constrained rotational freedom |
| 5748700, | May 10 1994 | Radiation therapy and radiation surgery treatment system and methods of use of same | |
| 5751781, | Oct 07 1995 | ELE KKTA AB | Apparatus for treating a patient |
| 5754622, | Jul 20 1995 | Siemens Medical Solutions USA, Inc | System and method for verifying the amount of radiation delivered to an object |
| 5835558, | Jul 09 1996 | Siemens Healthcare GmbH | Mobile x-ray exposure apparatus |
| 5848126, | Nov 26 1993 | Kabushiki Kaisha Toshiba | Radiation computed tomography apparatus |
| 5864597, | Apr 03 1996 | Toshiba Medical Systems Corporation | X-ray computed tomography device and method |
| 5877501, | Nov 26 1996 | Philips Electronics North America Corporation | Digital panel for x-ray image acquisition |
| 5912943, | Nov 26 1997 | Picker International, Inc. | Cooling system for a sealed housing positioned in a sterile environment |
| 5929449, | Jul 31 1995 | HANGER SOLUTIONS, LLC | Flat panel detector for radiation imaging with reduced electronic noise |
| 5949811, | Oct 08 1996 | Hitachi Medical Corporation | X-ray apparatus |
| 5966422, | Nov 02 1995 | PICKER MEDICAL SYSTEMS, LTD | Multiple source CT scanner |
| 5999587, | Jul 03 1997 | ROCHESTER, UNIVERSITY OF | Method of and system for cone-beam tomography reconstruction |
| 6031888, | Nov 26 1997 | Picker International, Inc.; PICKER INTERNATIONAL, INC | Fluoro-assist feature for a diagnostic imaging device |
| 6041097, | Apr 06 1998 | Picker International, Inc. | Method and apparatus for acquiring volumetric image data using flat panel matrix image receptor |
| 6113264, | Jun 04 1997 | Toshiba Medical Systems Corporation | X-ray diagnostic apparatus with C-shaped arms |
| 6148058, | Oct 23 1998 | Analogic Corporation | System and method for real time measurement of detector offset in rotating-patient CT scanner |
| 6152598, | Sep 02 1997 | Toshiba Medical Systems Corporation | R/F and chest radiography compatible X-ray imaging table |
| 6200024, | Nov 27 1998 | PICKER INTERNATIONAL, INC | Virtual C-arm robotic positioning system for use in radiographic imaging equipment |
| 6229870, | Nov 25 1998 | Picker International, Inc.; PICKER INTERNATIONAL, INC | Multiple fan beam computed tomography system |
| 6256370, | Jan 24 2000 | General Electric Company | Method and apparatus for performing tomosynthesis |
| 6259766, | Dec 16 1997 | U S PHILIPS CORPORATION | Computer tomography device |
| 6269143, | Aug 31 1998 | Shimadzu Corporation | Radiotherapy planning system |
| 6285739, | Feb 19 1999 | The Research Foundation of State University of New York | Radiographic imaging apparatus and method for vascular interventions |
| 6292534, | Dec 10 1997 | U.S. Philips Corporation | X-ray examination apparatus |
| 6307914, | Mar 12 1998 | Hokkaido University | Moving body pursuit irradiating device and positioning method using this device |
| 6318892, | Oct 28 1998 | Hitachi Medical Corporation | Radiography apparatus with rotatably supported cylindrical ring carrying image pickup unit |
| 6325537, | Oct 16 1998 | Kabushiki Kaisha Toshiba | X-ray diagnosis apparatus |
| 6345114, | Oct 27 1993 | Wisconsin Alumni Research Foundation | Method and apparatus for calibration of radiation therapy equipment and verification of radiation treatment |
| 6385286, | Aug 06 1998 | Wisconsin Alumni Research Foundation | Delivery modification system for radiation therapy |
| 6385288, | Jan 19 2001 | Mitsubishi Denki Kabushiki Kaisha | Radiotherapy apparatus with independent rotation mechanisms |
| 6389104, | Jun 30 2000 | Siemens Medical Solutions USA, Inc | Fluoroscopy based 3-D neural navigation based on 3-D angiography reconstruction data |
| 6393096, | May 27 1998 | Best Medical International, Inc | Planning method and apparatus for radiation dosimetry |
| 6435715, | Nov 30 1998 | Siemens Healthcare GmbH | Radiography device |
| 6463122, | Aug 21 2000 | Varian Medical Systems, Inc | Mammography of computer tomography for imaging and therapy |
| 6546073, | Nov 05 1999 | Georgia Tech Research Corporation | Systems and methods for global optimization of treatment planning for external beam radiation therapy |
| 6560311, | Aug 06 1998 | Wisconsin Alumni Research Foundation | Method for preparing a radiation therapy plan |
| 6582121, | Nov 15 2001 | GE Medical Systems Global Technology | X-ray positioner with side-mounted, independently articulated arms |
| 6618466, | Feb 21 2002 | ROCHESTER, UNIVERSITY | Apparatus and method for x-ray scatter reduction and correction for fan beam CT and cone beam volume CT |
| 6628745, | Jul 01 2000 | REVEAL IMAGING TECHNOLOGIES, INC | Imaging with digital tomography and a rapidly moving x-ray source |
| 6633627, | Sep 28 2000 | GE MEDICAL SYSTEMS GLOBAL TECHNOLOGY COMPANY, LLC, | X-ray CT system, gantry apparatus, console terminal, method of controlling them, and storage medium |
| 6661870, | Mar 09 2001 | MIDCAP FUNDING IV TRUST, AS SUCCESSOR TO EXISTING ADMINISTRATIVE AGENT | Fluence adjustment for improving delivery to voxels without reoptimization |
| 6707876, | May 22 2001 | GE Medical Systems Global Technology Company, LLC | X-ray CT apparatus and method |
| 6760402, | Aug 01 2002 | Siemens Medical Solutions USA, Inc. | Verification of mlc leaf position and of radiation and light field congruence |
| 6792074, | Mar 05 2001 | Brainlab AG | Method for producing or updating radiotherapy plan |
| 6842502, | Feb 18 2000 | WILLIAM BEAUMONT HOSPITAL | Cone beam computed tomography with a flat panel imager |
| 6865254, | Jul 02 2002 | C-Rad Innovation AB | Radiation system with inner and outer gantry parts |
| 6888919, | Nov 02 2001 | Varian Medical Systems, Inc | Radiotherapy apparatus equipped with an articulable gantry for positioning an imaging unit |
| 6907100, | Oct 25 2001 | Kabushiki Kaisha Toshiba | Cone beam type of X-ray CT system for three-dimensional reconstruction |
| 6915005, | Mar 09 2001 | MIDCAP FUNDING IV TRUST, AS SUCCESSOR TO EXISTING ADMINISTRATIVE AGENT | Method for reconstruction of limited data images using fusion-aligned reprojection and normal-error-aligned reprojection |
| 6980627, | Oct 06 2000 | NURAY TECHNOLOGY CO , LTD | Devices and methods for producing multiple x-ray beams from multiple locations |
| 6990175, | Oct 18 2001 | Toshiba Medical Systems Corporation | X-ray computed tomography apparatus |
| 6993112, | Mar 12 2002 | Deutsches Krebsforschungszentrum Stiftung Des Offentlichen Rechts | Device for performing and verifying a therapeutic treatment and corresponding computer program and control method |
| 7030386, | Oct 07 2002 | SUNNYBROOK HEALTH SCIENCES CENTRE; SUNNYBROOK AND WOMEN S COLLEGE HEALTH SCIENCES CENTRE | High quantum efficiency x-ray detector for portal imaging |
| 7062006, | Jan 19 2005 | AIRDRIE PARTNERS I, LP | Computed tomography with increased field of view |
| 7072436, | Aug 24 2001 | BOARD OF TRUSTEES OF THE LELAND STANFORD JUNIOR UNIVERSITY, THE | Volumetric computed tomography (VCT) |
| 7127035, | Aug 29 2001 | TOSHIBA ELECTRON TUBES & DEVICES CO , LTD | Rotary anode type X-ray tube |
| 7145981, | Aug 24 2001 | BOARD OF TRUSTEES OF THE LELAND STANFORD JUNIOR UNIVERSITY, THE | Volumetric computed tomography (VCT) |
| 7154991, | Oct 17 2003 | MIDCAP FUNDING IV TRUST, AS SUCCESSOR TO EXISTING ADMINISTRATIVE AGENT | Patient positioning assembly for therapeutic radiation system |
| 7170975, | Sep 16 2002 | Siemens Healthcare GmbH | Method for operating a computed tomography apparatus having a diaphragm at the radiation detector |
| 7193227, | Jan 24 2005 | Board of Regents, The University of Texas System | Ion beam therapy system and its couch positioning method |
| 7227923, | Apr 18 2005 | General Electric Company | Method and system for CT imaging using a distributed X-ray source and interpolation based reconstruction |
| 7227925, | Oct 02 2002 | Varian Medical Systems, Inc | Gantry mounted stereoscopic imaging system |
| 7280631, | Nov 26 2003 | General Electric Company | Stationary computed tomography system and method |
| 7305063, | Jul 18 2003 | Koninklijke Philips Electronics N.V. | Cylindrical x-ray tube for computed tomography imaging |
| 7388940, | Nov 24 2006 | General Electric Company; The Board of Trustees of the Leland Stanford Junior University | Architectures for cardiac CT based on area x-ray sources |
| 7428292, | Nov 24 2006 | General Electric Company | Method and system for CT imaging using multi-spot emission sources |
| 7471765, | Feb 18 2000 | WILLIAM BEAUMONT HOSPITAL | Cone beam computed tomography with a flat panel imager |
| 7496181, | Nov 28 2005 | The Board of Trustees of the Leland Stanford Junior University | X-ray collimator for imaging with multiple sources and detectors |
| 7657304, | Oct 05 2002 | Varian Medical Systems, Inc | Imaging device for radiation treatment applications |
| 7760849, | Apr 14 2006 | WILLIAM BEAUMONT HOSPITAL | Tetrahedron beam computed tomography |
| 7826592, | Feb 18 2000 | WILLIAM BEAUMONT HOSPITAL | Cone-beam computed tomography with a flat-panel imager |
| 7945021, | Dec 18 2002 | Varian Medical Systems, Inc | Multi-mode cone beam CT radiotherapy simulator and treatment machine with a flat panel imager |
| 8073104, | May 25 2006 | WILLIAM BEAUMONT HOSPITAL | Portal and real time imaging for treatment verification |
| 20030072407, | |||
| 20030095627, | |||
| 20030138077, | |||
| 20030191363, | |||
| 20030235271, | |||
| 20040002641, | |||
| 20040081270, | |||
| 20040086074, | |||
| 20040096033, | |||
| 20040120452, | |||
| 20040165696, | |||
| 20040174949, | |||
| 20040184578, | |||
| 20040254448, | |||
| 20050013404, | |||
| 20050027196, | |||
| 20050053189, | |||
| 20050054937, | |||
| 20050058237, | |||
| 20050080336, | |||
| 20050085710, | |||
| 20050111610, | |||
| 20050111616, | |||
| 20050111621, | |||
| 20050197564, | |||
| 20050234327, | |||
| 20050249432, | |||
| 20050251029, | |||
| 20060002506, | |||
| 20060008047, | |||
| 20060017009, | |||
| 20060239409, | |||
| 20060245543, | |||
| 20060259282, | |||
| 20060269049, | |||
| 20060274885, | |||
| 20060285639, | |||
| 20060285640, | |||
| 20060285841, | |||
| 20070003123, | |||
| 20070016014, | |||
| 20070019782, | |||
| 20070053492, | |||
| 20070076846, | |||
| 20070280408, | |||
| 20080031406, | |||
| 20090135994, | |||
| 20100008467, | |||
| 20100054410, | |||
| 20100119032, | |||
| 20100135454, | |||
| 20110002439, | |||
| 20110080992, | |||
| 20110211666, | |||
| 20130142310, | |||
| CN1419891, | |||
| CN1589744, | |||
| CN1723743, | |||
| CN1748217, | |||
| CN1758876, | |||
| DE1992708, | |||
| DE2822241, | |||
| EP314231, | |||
| EP922943, | |||
| JP10033520, | |||
| JP10113400, | |||
| JP10328318, | |||
| JP10511595, | |||
| JP11047290, | |||
| JP11160440, | |||
| JP11276463, | |||
| JP1199148, | |||
| JP2000126164, | |||
| JP2000308634, | |||
| JP4242736, | |||
| JP4307035, | |||
| JP5172764, | |||
| JP5252594, | |||
| JP56101579, | |||
| JP56168578, | |||
| JP58094835, | |||
| JP7255717, | |||
| JP8122438, | |||
| JP9218939, | |||
| JP9327453, | |||
| WO9713552, | |||
| WO9852635, | |||
| WO9903397, | |||
| WO160236, | |||
| WO2004061744, | |||
| WO2004061864, | |||
| WO2004080309, | |||
| WO2006018761, |
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