Geometrical arrangements of computed tomography system detectors for enhanced scan coverage and image quality

Abstract

One or more systems, method, and / or computer program products of use provided herein relate to generating CT images from data collected by X-ray detectors comprising alternate or asymmetric X-ray detector geometries, wherein the alternate or asymmetric X-ray detector geometries can provide a mechanism to increase scan coverage during CT imaging for faster scans. Embodiments described herein provide a framework to generate CT images with enhanced image quality parameters such as temporal, spectral, or spatial resolution, by employing the asymmetric X-ray detector geometries in conjunction with pre-patient collimator, pre-patient filter and post-patient filter geometries and image reconstruction techniques to optimally utilize the measurements acquired from the asymmetric X-ray detector geometries.

Description

GEOMETRICAL ARRANGEMENTS OF COMPUTED TOMOGRAPHY SYSTEMDETECTORS FOR ENHANCED SCAN COVERAGE AND IMAGE QUALITYCROSS-REFERENCE TO RELATED APPLICATIONS

[0001] This application claims priority to India Provisional Patent Application No. 202341066973 filed on October 5, 2023, entitled “ALTERNATE CT DETECTOR GEOMETRICAL ARRANGEMENTS FOR ENHANCED SCAN COVERAGE AND IMAGE QUALITY” The entireties of the aforementioned application are incorporated by reference herein.TECHNICAL FIELD

[0002] The subject disclosure generally relates to computed tomography (CT) imaging, and more specifically to alternated X-ray detector geometries for enhanced CT imaging.BACKGROUND

[0003] Medical imaging systems employed to obtain images of affected regions of a subject for diagnosing medical conditions can comprise ultrasound imaging systems, X-ray systems, CT imaging systems, magnetic resonance imaging (MRI) systems, single photon emission computed tomography (SPECT) systems, positron emission tomography (PET) systems, multi-modal imaging systems, etc. Such systems are widely known and employed across the globe to acquire image data of a subject and generate user viewable images. In CT imaging systems, X-rays can be passed in different directions through the body of a subject to obtain images of an internal volume of the subject.

[0004] The above-described background description is merely intended to provide a contextual overview regarding X-ray CT imaging systems and is not intended to be exhaustive.SUMMARY

[0005] The following presents a summary to provide a basic understanding of one or more embodiments described herein. This summary introduces concepts that are described in greater detail in the detailed description section. This summary is not intended to identify key or critical elements, delineate scope of particular embodiments or scope of claims. Thus, this summary should not be used to identify essential features of the claimed subject matter, nor to limit the scope of the claimed subject matter. Its sole purpose is to present concepts in a simplified form as a prelude to the more detailed description that is presented later. In one or more embodiments described herein, systems, methods, and / or computer program products thatcan generate CT images from sinogram data generated by a CT system comprising an X-ray detector with different geometries are discussed.

[0006] According to an embodiment, a CT system is provided. The CT system can comprise a hyper-collimation detector located inside a gantry of the CT system and across an X- ray source of the CT system. The hyper-collimation detector can comprise a first detector unit located on one side of an axis passing through a center of rotation of the gantry and running parallel to the gantry. The hyper-collimation detector can further comprise a second detector unit located on the opposite side of the axis and offset from the first detector unit along the axis. The hyper-collimation detector can further comprise a pre-patient collimator having a shape that is based on a geometry of the hyper-collimation detector to selectively expose active regions of the hyper-collimation detector to X-rays emitted from the X-ray source of the CT system to generate CT images. Collimation is defined as controlling the amount of X-ray radiation directed towards a subject being imaged by employing a pre-patient collimator. Collimation impacts the X-ray dose exposure and total scan time.

[0007] According to another embodiment, a method is provided. The method can comprise generating CT images of an entity by employing a CT system comprising a hypercollimation detector to differentially sample X-rays generated by an X-ray source of the CT system and attenuated by the entity, wherein the hyper-collimation detector can comprise a first detector unit located on one side of an axis passing through a center of rotation of a gantry of the CT system and running parallel to the gantry and a second detector unit located on the opposite side of the axis and offset from the first detector unit along the axis, where the first detector unit and the second detector unit are also located inside the gantry and across the X-ray source. The method can further comprise selectively exposing active regions of the hyper-collimation detector to the X-rays emitted from the X-ray source of the CT system by employing a pre- patient collimator, wherein the pre-patient collimator can be designed according to a geometry of the hyper-collimation detector.

[0008] According to yet another embodiment, a CT system is provided. The CT system can comprise a dual hyper-collimation detector located inside a gantry of the CT system and across an X-ray source of the CT system. The dual hyper-collimation detector can comprise a first detector unit located on one side of an axis passing through a center of rotation of the gantry and running parallel to the gantry, wherein the first detector unit can comprise a first detector region having a first material composition and a second detector region having a second material composition that can be different from the first material composition. The dual hyper-collimation detector can further comprise a second detector unit located on the opposite side of the axis and offset from the first detector unit along the axis, wherein the second detector unit can comprise athird detector region having the first material composition and a fourth detector region having the second material composition.

[0009] According to yet another embodiment, a method is provided. The method can comprise generating CT images of an entity by employing a CT system comprising a dual hypercollimation detector to differentially sample X-rays generated by an X-ray source of the CT system and attenuated by the entity, wherein the dual hyper-collimation detector can comprise a first detector unit located on one side of an axis passing through a center of rotation of a gantry of the CT system and running parallel to the gantry, wherein the first detector unit can comprise a first detector region having a first material composition and a second detector region having a second material composition that can be different from the first material composition, and a second detector unit located on the opposite side of the axis and offset from the first detector unit along the axis, wherein the second detector unit can comprise a third detector region having the first material composition and a fourth detector region having the second material composition. In some embodiments, the first detector unit and the second detector unit can comprise different respective material compositions, different respective structural constructions and / or different respective physical dimensions to enable differential sampling of the entity.

[0010] According to yet another embodiment a system is provided. The system can comprise a processor that can execute computer-executable components stored in memory, wherein the computer-executable components can comprise an image generation algorithm that can generate one or more CT images from X-rays detected by a detector of a CT system by combining respective sinograms generated by respective detector units of the detector, wherein the respective detector units can be asymmetrically positioned with respect to each other inside a gantry of the CT system to receive differentially sampled X-ray beams.

[0011] According to yet another embodiment, a computer-implemented method is provided. The computer-implemented method can comprise generating, by a system operatively coupled to a processor, one or more CT images from X-rays detected by a detector of a CT system by combining respective sinograms generated by respective detector units of the detector, wherein the respective detector units can be asymmetrically positioned with respect to each other inside a gantry of the CT system to receive differentially sampled X-ray beams.

[0012] According to yet another embodiment, a computer program product to generate CT images is provided. The computer program product can comprise a non-transitory computer readable memory having program instructions embodied therewith, the program instructions executable by a processor to cause the processor to generate one or more CT images from X-rays detected by a detector of a CT system by combining respective sinograms generated by respective detector units of the detector, wherein the respective detector units can beasymmetrically positioned with respect to each other inside a gantry of the CT system to receive differentially sampled X-ray beams.BRIEF DESCRIPTION OF THE DRAWINGS

[0013] One or more embodiments are described below in the Detailed Description section with reference to the following drawings:

[0014] FIG. 1 illustrates a diagram of an example, non-limiting CT system that can perform CT imaging in accordance with one or more embodiments described herein.

[0015] FIG. 2 illustrates a block diagram of an example, non-limiting CT system comprising a CT scanning machine coupled to an operator console in accordance with one or more embodiments described herein.

[0016] FIG. 3 illustrates a diagram of an example, non-limiting X-ray detector employed in a CT system in accordance with one or more embodiments described herein.

[0017] FIG. 4 illustrates a diagram of an example, non-limiting axial scan plane geometry of a CT system in accordance with one or more embodiments described herein.

[0018] FIG. 5 illustrates a block diagram of an example, non-limiting system to generate CT images from sinogram data generated by a detector of a CT system in accordance with one or more embodiments described herein.

[0019] FIG. 6 illustrates diagrams of example, non-limiting configurations of an X-ray detector in a CT system in accordance with one or more embodiments described herein.

[0020] FIG. 7 illustrates diagrams of example, non-limiting configurations of a prepatient collimator in accordance with one or more embodiments described herein.

[0021] FIG. 8 illustrates diagrams of example, non-limiting configurations of an X-ray detector in a CT system in accordance with one or more embodiments described herein.

[0022] FIG. 9 illustrates diagrams of example, non-limiting configurations of a prepatient filter or a post patient filter in accordance with one or more embodiments described herein.

[0023] FIG. 10 illustrates diagrams of example, non- limiting configurations of a CT detector mounted on an electromechanical assembly in accordance with one or more embodiments described herein.

[0024] FIG. 11 illustrates diagrams of example, non-limiting scan planes with X-ray beams for redundant samples and conjugate samples in accordance with one or more embodiments described herein.

[0025] FIG. 12 illustrates a flow diagram of an example, non-limiting method to generate imaging data from a CT system by selectively exposing an X-ray detector of the CT system to X- rays in accordance with one or more embodiments described herein.

[0026] FIG. 13 illustrates flow diagrams of example, non-limiting methods to generate CT images by employing a CT system in accordance with one or more embodiments described herein.

[0027] FIG. 14 illustrates a flow diagram of an example, non-limiting method to generate CT images by employing a CT system comprising a hyper-collimation detector in accordance with one or more embodiments described herein.

[0028] FIG. 15 illustrates a diagram of an example, non-limiting method to generate CT images by employing a CT system comprising a dual hyper-collimation detector in accordance with one or more embodiments described herein.

[0029] FIG. 16 illustrates a diagram of an example, non-limiting method to generate CT images by employing an image generation algorithm in accordance with one or more embodiments described herein.

[0030] FIG. 17 illustrates a block diagram of an example, non-limiting operating environment in which one or more embodiments described herein can be facilitated.

[0031] FIG. 18 illustrates an example networking environment operable to execute various implementations described herein.

[0032] It is to be appreciated that the figures illustrated in the drawings are not to scale. Wherever possible, the same reference numbers have been used throughout the drawings and the accompanying written description to refer to the same or like parts.DETAILED DESCRIPTION

[0033] The following detailed description is merely illustrative and is not intended to limit embodiments and / or application or uses of embodiments. Furthermore, there is no intention to be bound by any expressed or implied information presented in the preceding Background or Summary sections, or in the Detailed Description section.

[0034] One or more embodiments are now described with reference to the drawings, wherein like referenced numerals are used to refer to like elements throughout. In the following description, for purposes of explanation, numerous specific details are set forth in order to provide a more thorough understanding of the one or more embodiments. It is evident, however, in various cases, that the one or more embodiments can be practiced without these specific details.

[0035] Medical conditions can be diagnosed by employing various medical imaging systems and methods to obtain images of affected regions of a subject (e.g., a patient). Medical imaging systems employed to diagnose certain medical conditions can comprise, for example, ultrasound imaging systems, X-ray systems, CT imaging systems, MRI systems, SPECT systems, PET systems, multi-modal imaging systems, etc. These and other systems are most widely known and employed across the globe to acquire image data of a subject and generate user viewable images.

[0036] Imaging a subject by employing a medical imaging system such as a CT imaging system, or an MRI system can involve positioning the subject over a table and moving the table inside a gantry of the imaging system during imaging. In case of CT imaging systems, X-rays can be passed in different directions through the body of a subject to obtain images of one or more internal volumes of the subject. A CT imaging system typically comprises an X-ray generator that powers an X-ray tube of the CT imaging system to emit the X-rays that are directed onto the body of the subject positioned in a gantry of the CT imaging system. Further, an X-ray detector is positioned in the gantry to detect the X-rays. Upon emission of the X-rays, the X-rays can get transmitted transversely through a portion of the subject’s anatomy and become attenuated. The attenuated X-rays are detected by the X-ray detectors. The X-rays detected by the X-ray detector are processed via various image reconstruction and visualization techniques to generate a user viewable image associated with the subject such as, for example, of one or more internal volumes of interest of the subject. To generate CT images, a CT imaging system utilizes a series of X-ray projections, also known as views, that are acquired at different angles, axially, and through a slice or a thin cross-sectional area of the subject. Each projection can comprise a series of discrete samples of X-rays. Attenuation coefficients can be determined for respective discrete samples of the X-rays, followed by reconstruction of a CT image of the patient’s anatomy.

[0037] In existing CT imaging systems, the coverage of a single axial scan (e.g., in mm per turn of a gantry) is determined by the number of detectors stacked along the Z-axis of an X- Y-Z plane of the Cartesian coordinate system, wherein the Z-axis for a CT imaging system can be parallel to the table of the CT imaging system on which the subject can be positioned during scanning. CT imaging systems also employ a pre-patient collimator that ensures that X-rays that project onto areas of the CT imaging system where the detector is absent are blocked and the rest of the X-rays are allowed to pass through the subject, thereby ensuring that only a certain region of the subject’s body is exposed to X-rays. The phenomenon of exposing only specific regions of the subject to the X-rays during an axial scan is referred to as collimation, and the corresponding opening of the pre-patient collimator that allows X-rays to selectively pass through the subjectonto the X-ray detector is referred to as the aperture of the pre-patient collimator. To increase the collimation, CT imaging systems can comprise multiple detectors stacked along the Z-direction.

[0038] Embodiments described herein include systems, methods, and computer program products that can employ alternate X-ray detector geometries or arrangements in a CT imaging system to enhance X-ray scan coverage during CT imaging and to improve image quality of the CT images thus generated, by enhancing temporal, spatial, and / or spectral resolution of the CT imaging system in comparison to a conventional CT imaging system (i.e., a CT imaging system employing a conventional detector geometry, such as illustrated in FIG. 3), at an equivalent X- ray dose. It is to be appreciated that the terms “CT imaging system(s),” “CT system(s),” “CT scan device(s),” and “CT scanner(s)” are used interchangeably throughout this specification. In this regard, a CT imaging system can generally refer to a CT scanning apparatus coupled to a computing system that can scan a subject (e.g., human or animal subject) or object (e.g., inanimate objects such as phantoms) and generate CT images based on the scanning. It is to be further appreciated that the terms “X-ray(s),” “X-ray beam(s),” and “X-ray radiation beam(s)” are also used interchangeably throughout this specification.

[0039] In accordance with one or more aspects of the present disclosure, a system can be provided to enhance temporal, spatial, or spectral resolution of CT images as compared to CT images generated by a conventional CT imaging system at an equivalent X-ray dose. The system can comprise an X-ray source configured to generate an X-ray beam that can be directed towards a subject and an X-ray detector configured to detect the X-ray beam after attenuation of the X-ray beam by the subject. In some embodiments, the system can further comprise an X-ray detector configured to be disposed in an asymmetric-offset configuration, referred to as a hypercollimation arrangement, thereby increasing the effective collimation and the temporal resolution of the CT system beyond those of a conventional X-ray detector arrangement (e.g., such as that of non- limiting X-ray detector 300). In various embodiments, the system can further comprise a pre-patient collimator to selectively expose only the hyper-collimation detector to the X-ray beam and block the remaining X-ray beam, to maintain the same X-ray dose equivalence as that employed in conjunction with a conventional CT detector, while increasing the effective collimation of the CT imaging system. In other embodiments, the X-ray detector can comprise two sets of hyper-collimation detectors that can be laterally inverted and juxtaposed with respect to each other in an arrangement referred to as a dual-hyper-collimation arrangement. The two sets of hyper-collimation detectors can comprise different respective characteristics such as different detector dimensions (e.g., physical dimensions of detector cells, structural construction of the two sets of hyper-collimation detectors, etc.) and different detector materials (e.g., material compositions of respective sets of hyper-collimation detectors). Furthermore, a pre-patient filteror a post-patient filter composed of a single material or two materials and arranged in the dual- hyper-collimation arrangement can be employed in the CT imaging system. The X-ray detector can be mounted on an electromechanical assembly that can dynamically adjust the detector subarrays of the X-ray detector to generate various configurations of the X-ray detector. The dual hyper-collimation detector can be employed individually or in conjunction with the prepatient filter and / or post-patient filter for a scan to enhance the spatial and / or spectral resolution of the CT imaging system to generate CT images, at an equivalent dose employed by a CT imaging system employing a conventional X-ray detector (e.g., such as non-limiting X-ray detector 300) for the same type of scan.

[0040] In accordance with an aspect of the present disclosure, a computer-implemented method can be provided to increase the collimation of a CT imaging system. The computer- implemented method can comprise rotating an X-ray source and an X-ray detector around a subject by employing a processor. The computer-implemented method can further comprise selectively exposing one or more detector subarrays of the X-ray detector to the X-ray beam generated by the X-ray source. The computer-implemented method can further comprise blocking a shadow area from the X-ray beam by employing a pre-patient collimator and acquiring data from the X-ray detector. The computer-implemented method can further comprise combining data generated by respective detector subarrays of the X-ray detector and reconstructing one or more images based on the combined data to enhance image quality parameters such as temporal, spatial, or spectral resolution.

[0041] It should be understood that the brief description above is provided to introduce in simplified form, a selection of concepts that are described in greater detail hereinafter. It is not meant to identify key or essential features of the claimed subject matter, the scope of which is defined uniquely by the claims that follow the detailed description. Furthermore, the claimed subject matter is not limited to implementations that solve any disadvantages noted above or in any part of this disclosure.

[0042] In the following detailed description, reference is made to the accompanying drawings that form a part hereof, and in which is shown by way of illustration, specific examples that may be practiced. These examples are described in sufficient detail to enable one skilled in the art to practice the subject matter, and it is to be understood that other examples may be utilized, and that logical, mechanical, electrical and other changes may be made without departing from the scope of the subject matter of this disclosure. The following detailed description is, therefore, provided to describe an exemplary implementation and not to be taken as limiting on the scope of the subject matter described in this disclosure. Certain features fromdifferent aspects of the following description may be combined to form yet new aspects of the subject matter discussed below.

[0043] When introducing elements of various examples of the present disclosure, the articles “a,” “an,” “the,” and “said” are intended to mean that there are one or more of the elements. The terms “comprising,” “including,” and “having” are intended to be inclusive and mean that there may be additional elements other than the listed elements.

[0044] As used herein, the term “computer” and related terms, e.g., “computing device”, “computer system” “processor”, “controller” are not limited to integrated circuits referred to in the art as a computer, but broadly refer to at least one microcontroller, microcomputer, programmable logic controller (PLC), application specific integrated circuit, and other programmable circuits, and these terms are used interchangeably herein.

[0045] Approximating language, as used herein throughout the specification and claims, may be applied to modify any quantitative representation that could permissibly vary without resulting in a change in the basic function to which it is related. Accordingly, a value modified by a term or terms, such as “about” and “substantially”, are not to be limited to the precise value specified. In at least some instances, the approximating language may correspond to the precision of an instrument for measuring the value. Here and throughout the specification and claims, range limitations may be combined and / or interchanged, such ranges are identified and include all the sub-ranges contained therein unless context or language indicates otherwise.

[0046] As used herein, the terms “systems”, “devices” and “apparatuses are interchangeable and include components, sub-components, sub-systems that include without limitation the medical imaging devices.

[0047] While certain examples are described below in the context of medical or healthcare systems, other examples can be implemented outside the medical environment.

[0048] It is to be appreciated that FIGs. 1 - 4 generally describe the components and / or operations of a CT imaging system that can employ the herein proposed geometries for an X-ray detector in conjunction with the herein proposed image processing algorithms to generate CT images. For example, in various embodiments described herein, an X-ray detector can comprise different geometries that when employed in a CT system for CT imaging, can provide an increased collimation and a faster scan time as compared to a conventional X-ray detector (e.g., such as non-limiting X-ray detector) employed by the CT system, for an equivalent X-ray dosage. Further, data from the X-ray detector can be processed by a computer algorithm to generate CT images with improved temporal resolution as compared to CT images that can be generated by the CT system with the conventional X-ray detector, for an equivalent X-raydosage. These embodiments are described in greater detail infra with reference to at least FIGs.5 - 18.

[0049] The embodiments depicted in one or more figures described herein are for illustration only, and as such, the architecture of embodiments is not limited to the systems, devices and / or components depicted therein, nor to any particular order, connection and / or coupling of systems, devices and / or components depicted therein. For example, in one or more embodiments, the non-limiting systems described herein, such as non-limiting system 500 as illustrated at FIG. 5, and / or systems thereof, can further comprise, be associated with and / or be coupled to one or more computer and / or computing-based elements described herein with reference to an operating environment, such as the operating environment 1700 illustrated at FIG. 17. For example, non-limiting system 500 can be associated with, such as accessible via, a computing environment 1700 described below with reference to FIG. 17, such that aspects of processing can be distributed between non-limiting system 500 and the computing environment 1700. In one or more described embodiments, computer and / or computing-based elements can be employed in connection with implementing one or more of the systems, devices, components and / or computer-implemented operations shown and / or described in connection with FIG. 5 and / or with other figures described herein.

[0050] FIG. 1 illustrates a diagram of an example, non-limiting CT system 100 that can perform CT imaging in accordance with one or more embodiments described herein.

[0051] In accordance with one or more embodiments of the present disclosure, FIG. 1 illustrates non-limiting CT system 100 that can be an exemplary CT imaging system configured to perform CT imaging. Particularly, non-limiting CT system 100 can be configured to image subject 106. In some embodiments, subject 106 can be a human or animal subject or patient, such as illustrated in FIG. 1. In other embodiments, subject 106 can be an inanimate object. For example, subject 106 can be a patient, one or more manufactured parts, and / or foreign objects such as dental implants, stents, and / or contrast agents present within the body of a subject. Nonlimiting CT system 100 can also be employed to scan three-dimensional (3D) structures with predefined geometries and material properties, known as phantoms.

[0052] In various embodiments, non-limiting CT system 100 can comprise gantry 102 that can further comprise at least one X-ray source 104 configured to project X-ray radiation beam(s) 206 (illustrated in FIG. 2) to perform CT imaging of subject 106. Subject 106 can be positioned on table 108 during the CT imaging. It is to be appreciated that the table of a CT imaging system for positioning subject 106 can also be referred to as a cradle or bed in one or more embodiments. Specifically, X-ray source 104 can be configured to project X-ray radiation beam(s) 206 towards detector 208 positioned on the opposite side of gantry 102 from X-raysource 104. Detector 208 can be an X-ray detector. Although FIG. 1 depicts only a single X-ray source 104, in some embodiments, multiple X-ray sources and detectors can be employed to project a plurality of X-ray radiation beams 206 to acquire projection data at different energy levels corresponding to subject 106. For example, in one or more embodiments, two sets of X- ray sources and detectors can be employed to generate dual-energy projections, with one set operating at a low kilovoltage (kVp) value and another set operating at a high kVp value. It should thus be appreciated that the methods described herein can be implemented with single energy acquisition techniques as well as dual energy acquisition techniques. In some embodiments, X-ray source 104 can enable dual-energy gemstone spectral imaging (GSI) by rapid peak kilovoltage (kVp) switching. Further, in some embodiments, detector 208 can be a photon-counting detector capable of differentiating X-ray photons of different energies.

[0053] In some configurations of non- limiting CT system 100, X-ray source 104 can project a cone-shaped X-ray radiation beam (e.g., X-ray radiation beam 206) that can be collimated to lie within an X-Y-Z plane of a Cartesian coordinate system, generally referred to as an "imaging plane." The X, Y and Z axes of the imaging plane are illustrated at least in FIG. 2, and the references to the individual axes throughout this specification are consistent with the orientation illustrated in FIG. 2. In various embodiments, X-ray radiation beam 206 can pass through a subject being imaged (e.g., subject 106), and after being attenuated by the subject, X- ray radiation beams 206 can impinge upon detector 208. The intensity of the attenuated X-ray radiation beams received at detector 208 can be dependent upon the attenuation of X-ray radiation beams 206 by the subject. In a non-limiting example, detector 208 can produce an electrical signal indicative of measurements of the X-ray beam attenuation at detector 208. A CT imaging system can measure attenuation along the path of an X-ray beam between an X-ray source and a detector.

[0054] FIG. 2 illustrates a block diagram of an example, non-limiting CT system 200 comprising a CT scanning machine coupled to an operator console in accordance with one or more embodiments described herein. Repetitive description of like elements and / or processes employed in respective embodiments is omitted for sake of brevity.

[0055] In accordance with one or more embodiments of the present disclosure, FIG. 2 illustrates non-limiting CT system 200 that can be an exemplary CT imaging system that can perform CT imaging. In various embodiments, non-limiting CT system 200 can comprise and / or be similar to non- limiting CT system 100 of FIG. 1. In accordance with various aspects of the present disclosure, non-limiting CT system 200 can be configured to perform CT imaging of entity 204. In various embodiments, entity 204 can be a human or animal subject or patient, or entity 204 can be an inanimate object. For example, entity 204 can be a patient, a phantom, oneor more manufactured parts, and / or foreign objects such as dental implants, stents, and / or contrast agents present within the body of a subject, and entity 204 can be analogous to subject 106 of FIG. 1. In accordance with various aspects of the present disclosure, non-limiting CT system 200 can comprise detector 208. Detector 208 can further comprise an array of detectors comprising a plurality of detector elements 202 that can collectively sense X-ray radiation beam 206, after X-ray radiation beam passes through entity 204, to acquire the corresponding projection data. The plurality of detector elements 202 can be arranged in a monotonous curve or a piecewise linear pattern along the X-axis with reference to the imaging plane, as illustrated in FIG. 3. Accordingly, in a non-limiting example, detector 208 can be fabricated in a multi-slice configuration including the plurality of rows of detector elements 202. In such a configuration, one or more additional rows of detector elements 202 can be arranged in a parallel configuration, as illustrated in FIG. 3, for acquiring the projection data. It is to be appreciated that the terms “detector cell(s)” and “detector element(s)” are used interchangeably throughout this specification.

[0056] According to an aspect of the present disclosure, non-limiting CT system 200 can be configured to traverse different angular positions around entity 204 to acquire desired projection data. Accordingly, in a non-limiting example, gantry 102 and the components mounted to gantry 102 can be configured to rotate about center of rotation 234 to acquire the projection data, for example, at different energy levels. Alternately, in another non-limiting example, where a projection angle of X-ray radiation beams 206 relative to entity 204 can vary as a function of time, the components mounted to gantry 102 can be configured to move along a general curve / curved trajectory rather than along a segment of a circle. The curved trajectory can indicate a spiral trajectory of data acquisition. That is, although gantry 102 remain stationary along the Z-axis while rotating around the Z-axis in a circular path (e.g., with reference to a unit circle, the trajectory of gantry 102 along the Z-axis can be a spiral due to movement of the table or cradle (e.g., tabled 08) along the Z-axis in a helical operation mode of non-limiting CT system 200. Stated differently, the trajectory of gantry 102 need not be circular as in an axial step and shoot mode or cine mode of operation of non-limiting CT system 200, wherein gantry 102 can rotate without movement of the table.

[0057] During imaging, X-ray source 104 and detector 208 can rotate along with gantry 102, and detector 208 can collect data of the attenuated X-ray beams. The data collected by detector 208 can undergo pre-processing and calibration (e.g., via a computing system) to condition the data and generate new data representing line integrals of attenuation coefficients associated with entity 204 being scanned. The processed data are commonly called projections. According to an aspect of the disclosure, the individual detector elements 202 of detector 208 cancomprise photon-counting detectors that can register the interactions of individual photons into one or more energy bins of detector 208. It should be appreciated that the methods described herein can also be implemented with energy-integrating detectors.

[0058] According to an aspect of the present disclosure, non-limiting CT system 200 can employ control mechanism 228 to control movement of various components of non-limiting CT system 200, such as the rotation of gantry 102 and the operation of X-ray source 104. In one or more aspects of the present disclosure, control mechanism 228 can employ X-ray controller 210 configured to provide power and timing signals to X-ray source 104. Control mechanism 228 can further employ gantry motor controller 212 configured to control a rotational speed and / or position of gantry 102 based on imaging requirements.

[0059] According to an aspect of the present disclosure, control mechanism 228 in conjunction with data acquisition system (DAS) 214 can be configured to sample analog data received from detector elements 202 and convert the analog data to digital signals for subsequent processing. DAS 214 can be further configured to selectively aggregate analog data from a subset of detector elements 202. The data sampled and digitized by DAS 214 can be transmitted to a computer or computing device 216. In various embodiments, computing device 216 can store the data in a storage device or mass storage 218. Mass storage 218, for example, can include a hard disk drive, a floppy disk drive, a compact disk-read / write (CD-R / W) drive, a Digital Versatile Disc (DVD) drive, a flash drive, and / or a solid-state storage drive.Additionally, computing device 216 can provide commands and parameters to one or more of the DAS 214, X-ray controller 210, and gantry motor controller 212 for controlling system operations such as data acquisition and / or processing. In one or more aspects of the present disclosure, computing device 216 can control system operations of non-limiting CT system 200 based on an operator input. For example, computing device 216 can receive the operator input including commands and / or scanning parameters via operator console 220 operatively coupled to computing device 216 and display 222. Operator console 220 can include a keyboard (not illustrated) or a touchscreen to allow the operator to specify the commands and / or scanning parameters. Although FIG. 2 illustrates only one operator console 220, more than one operator console can be coupled to non-limiting CT system 200, for example, for inputting or outputting system parameters, requesting examinations, plotting data, and / or viewing images. Further, in a non-limiting example, non-limiting CT system 200 can be coupled to multiple displays, printers, workstations, and / or similar devices located either locally or remotely, for example, within an institution or hospital, or in an entirely different location via one or more configurable wired and / or wireless networks such as the Internet and / or virtual private networks, wireless telephonenetworks, wireless local area networks, wired local area networks, wireless wide area networks, wired wide area networks, etc.

[0060] According to an aspect of the present disclosure, non-limiting CT system 200 can either comprise or be coupled to Picture Archiving and Communications system (PACS) 224. In an exemplary implementation, PACS 224 can be further coupled to a remote system such as a radiology department information system, hospital information system, and / or to an internal or external network (not illustrated) to allow operators at different locations to supply commands and parameters and / or gain access to the image data. Computing device 216 can employ the operator-supplied and / or system-defined commands and parameters to operate table motor controller 226 that can control table 108 and image reconstructor 230. Table 108 can be a motorized table. Specifically, table motor controller 226 can move table 108 for appropriately positioning entity 204 in gantry 102 for acquiring projection data corresponding to the target volume of entity 204. In non-limiting CT system 100 and non-limiting CT system 200, gantry 102 can be rotated by 360 degrees (360°), and data from detector 208 can be acquired T times to generate P projections, wherein T and P represent positive numeric value.

[0061] The various methods and processes described herein can be stored as executable instructions in a non-transitory memory on a computing device (or controller) in non-limiting CT system 200.

[0062] FIG. 3 illustrates a diagram of an example, non-limiting X-ray detector 300 employed in a CT system in accordance with one or more embodiments described herein. Repetitive description of like elements and / or processes employed in respective embodiments is omitted for sake of brevity.

[0063] In FIG. 3, non- limiting X-ray detector 300 is presented as an example of a conventional X-ray detector and as a reference to describe the configurations for detector 208 and the corresponding advantages proposed by embodiments of the present disclosure. In accordance with one or more aspects of the present disclosure, FIG. 3 illustrates a conventional configuration of detector 208 that can be employed in CT systems such as non- limiting CT system 100 and / or non- limiting CT system 200. Non- limiting X-ray detector 300 can comprise a plurality of detector subarrays, such as detector subarray 306 and detector subarray 308, that can be arranged symmetrically about central axis 312. Detector subarrays 306 and 308 can comprise multiple rows, such as row 302 and row 304. In a conventional X-ray detector such as non-limiting X-ray detector 300, the subarrays can be identical to each other.

[0064] In accordance with an aspect of the present disclosure, detector subarrays 306 and 308 can further comprise individual units called detector cells 310. In accordance with an aspect of the present disclosure, detector cells 310 can be arranged in an M x N grid spanning the Z-Xplane of the Cartesian coordinate system referenced herein, and each detector cell of detector cells 310 can have a size m x n, wherein m and n can be positive numeric values. For example, detector cells 310 can be arranged in M rows, and each of the detector cells 310 in the M rows can have a width m in the Z-axis direction. Detector cells 310 can be further arranged in N columns and each of the detector cells 310 in the N columns can have a length n in the X-axis direction. The width m and the length n of a detector cell can be in millimeters (mm). In accordance with an aspect of the present disclosure, the plurality of detector subarrays 306 and 308 can be located equally on both sides of central axis 312, wherein central axis 312 can be parallel to the Z-axis. Central axis 312 can comprise a detector isocenter (ISO). The detector ISO can be defined as a point or a plurality of points along the Z-axis about which detector subarrays 306 and 308 can be symmetrically arranged with respect to each other. That is, the ISO can fall under center of rotation 234 in the X-Y plane, and the ISO can be a virtual location in space around which gantry 102 and the components mounted on gantry 102 can spin during imaging. Center of rotation 234 can be located in the hollow part of the central bore of gantry 102 within which an entity (e.g., subject 106, entity 204, etc.) can be positioned during CT imaging.

[0065] The resolutions of the CT system in the Z-direction and the X-direction can be dependent on the width m and the length n of detector cells 310, respectively. In accordance with an aspect of the present disclosure, the coverage per axial scan in the Z-direction and in the X- direction can be determined by (Mxm) and (Nxn), respectively. In order to scan the entity for adistance L along the Z-axis, S axial scans can be conducted, wherein S = — - — . Further, the total time required to scan the subject for the distance L can be represented by SxT, wherein T can represent the time per axial scan. Time T can include a scan time and a delay associated with the movement of table 108 onto which the entity can be placed for the purpose of scanning. In some scenarios, a longer duration for the scans can increase the possibilities of motion and breathing related artifacts and may also increase the dose administered to a patient.

[0066] In various embodiments, a higher collimation system can be desirable because such a system can reduce the duration of scans and can also reduce the possibilities of motion- induced artifacts. Typical examples of human anatomies requiring wider collimation to reduce motion-induced artifacts include, the heart, the chest, etc. A wider collimation can also assist in understanding the function of an anatomy over a period of time, which can be studied by rotating gantry 102 for multiple rotations around the entity while keeping table 108 stationary. Such a mode of scanning is called a cine mode. Further, wider collimation can assist in reducing the motion-induced artifacts and cover larger volumes. A CT system that does not employ fast or slow kV-s witching or any special pre -patient filter or post-patient filter, can acquire two axialscans at the same location on the entity at two kVp settings to obtain material-decomposition (MD) images. Such a scanning mechanism is referred to as rotate-rotate scan in the art. Such a scanning mechanism can involve poor temporal resolution and higher dose exposure for an entity being scanned due to the need for two axial scans at the same location on the entity’s body. The size in terms of m x n of a detector cell can govern the achievable resolution for detector 208 and the detector geometric efficiency (DGE) of detector 208, for a given detector material. DGE can be defined as a ratio of an active area (i.e., detector elements exposed to X-rays) of a detector of a CT system to the total area of the detector exposed to the X-rays. Lower values of m and n can generate better Z-axis and in-plane resolutions with a poor DGE, whereas higher values of m and n can generate poor Z-axis and in-plane resolutions with a good DGE. The DGE of detector 208 can determine the signal-to-noise ratio (SNR) of the resultant CT images, and there can be tradeoff between resolution and SNR for a given detector material.

[0067] The usage of components such as an X-ray tube (e.g., inside X-ray source 104) and detector 208 of the CT system can depend on the number of scans S to cover the distance L. Thus, for a CT system with a lower scan coverage, the value of S can be higher as compared to that of a CT system with higher scan coverage. The usage of the components over time can also lead to wear-and-tear of the components and reduced life of the components. Thus, the life of components in a CT system with a lower scan coverage can be lower than that in a CT system with a higher scan coverage.

[0068] As described supra, L can represent the amount of traversal needed to scan an entity (e.g., a portion of an anatomy or an inanimate object). In other words, L can represent the total length of scanning / amount of scan length / amount of motion of table 108 on which the entity can be positioned during scanning. Typically, L can be greater than (M x m), wherein (M x tri) represents the length (in mm) of detector 208 and the collimation along the Z-axis. For example, for scanning an object for 100 mm along the Z-axis, a CT system with a 20 mm collimation along the Z-axis can employ 5 scans (i.e., S = 100mm / 20mm). A higher collimation (M x m) can reduce the scan time for a particular scan length L. L is typically controlled by an operator of the CT system and can be different for different anatomies and entities (e.g., depending on the part of the body begin scanned). An operator of the CT machine (e.g., hardware, software, Al, neural network, machine and / or user) can set the value of L prior to a scan. The value of L can remain fixed throughout a scan; however, the value of L can change for subsequent scans. Multiple scans can be administered to the same patient based on the clinical needs of the patient, and L can vary per scan. Once the L is defined for a particular scan, data acquisition via the CT system can begin..

[0069] In various embodiments, L can be computed with reference to a position on the entity, commonly referred as landmarking position, and the position of table 108 can be automatically transformed with reference to the landmarking position on the entity, before L can be assigned. The landmarking position can correspond to a zero (0) position along the Z-axis. After determining the landmarking position as part of the workflow for the patient, the starting and ending position for a scan can be defined by an operator (e.g., hardware, software, Al, machine, neural network and / or user) of the CT system, with reference to the landmarking position. The CT system can internally encode the starting and ending positions on table 108 and feed the information to table motor controller 226 that can control table 108 to reposition the subject by moving the starting position on the patient to the zero (0) position, along the Z-axis. After repositioning the patient, the CT scanning can begin wherein X-rays can be emitted from X-ray source 104, and table 108 can move along the Z-axis to feed the patient into gantry 102. The movement of table 108 and the X-ray emission can stop once table 108 reaches the ending position.

[0070] The CT system can employ different modes of operations, involving different respective mechanisms with respect to the movement of table 108 and the X-ray control on gantry 102 to acquire different types of data for different clinical purposes. For example, the CT system can operate in an axial step and shoot mode, where the entity and table 108 can remain stationary during the CT imaging, and gantry 102 can turn the X-ray emissions on and off. X-ray source 104 can turn at a particular angle (e.g., between 0° and 360°) and complete one turn of scanning, after which gantry 102 can turn off the X-ray emission to stop the scanning. Gantry 102 can continue to spin at a constant rotational rate and table 108 can be controlled (e.g., by table motor controller 226) to feed the subject through gantry 102 in defined distance increments along the Z-axis, based on a distance programmed into the CT system. Thereafter, gantry 102 can turn the X-ray emission on and X-ray source 104 can complete an additional turn of scanning. The process can be repeated until the scanning is completed. In the axial step and shoot mode, data from the scanning can be acquired in slabs and combined to generate CT images for a defined length of L.

[0071] The CT system can also operate in a helical or spiral mode, wherein the X-ray emission can be turned on at the beginning position of table 108 (e.g., based on the landmarking position), and table 108 can be gradually fed (e.g., by table motor controller 226) through gantry 102 during the scanning. The X-ray emission can remain on throughout the scan until the scanning is completed and table 108 has reached the ending position. The helical or spiral mode can result in the helical trajectory of data acquisition as described elsewhere herein.

[0072] Further, the CT system can operate in the cine mode or fluoroscopy mode described elsewhere herein. In the cine mode, gantry 102 can rotate during scanning and table 108 can remain stationary. Additionally, the X-ray emission can remain on beyond one turn of scanning, such that the same location on the entity can be repeatedly scanned to check for any movement of a contrast through an area of interest of the entity. Thus, the contrast can flow into and wash through a portion of the entity’s anatomy before flowing out, and the evolution of the contrast over time can be observed via the cine mode. The same portion of the entity’s anatomy can be repeatedly imaged.

[0073] In various embodiments, with reference to the three modes of CT imaging discussed herein, the pre-patient collimation can be set independently of the scan length L. Accordingly, in various embodiments, the X-ray detector can be reconfigured for different lengths (M X m) and different types of collimations to achieve different values for S (i.e., the number of scans) for a defined value of L.

[0074] FIG. 4 illustrates a diagram of an example, non-limiting axial scan plane geometry 400 of a CT system in accordance with one or more embodiments described herein. Repetitive description of like elements and / or processes employed in respective embodiments is omitted for sake of brevity.

[0075] In accordance with one or more aspects of the present disclosure, FIG. 4 illustrates a scan plane of a CT imaging system (e.g., non-limiting CT system 100 and / or non-limiting CT system 200) X-ray tube 402 and bowtie filter 404. Bowtie filter 404 can be a pre-patient filter.In a detector array, a single detector cell can be referred to as a channel. In this regard, a channel angle, y, can be defined as an angle formed between a line (e.g., line 406) extending from a focal spot of X-ray tube 402 of X-ray source 104 to a detector cell of an array of detector 208 and a line (e.g., line 408) extending from the focal spot of X-ray tube 402 to the ISO of the CT imaging system. A projection angle or view angle, , can be defined as an angle formed between a line (e.g., line 408) joining the focal spot of X-ray tube 402 to the ISO of the CT imaging system and the Y-axis. The channel angle and projection angle are illustrated in FIG. 4. Every row of detector 208 can collect a sample for all views (X-ray projections) during a complete 2rt radian rotation (i.e., a 360° rotation) of gantry 102, and the sample can be termed as a sinogram generated by the CT imaging system. The sinogram can be utilized in filtered back-projection (FBP) techniques to reconstruct CT images of a scanned object using an axial scan of 2TI radians.

[0076] In some non-limiting embodiments, a rotation of only n + F radians of gantry 102 can be sufficient for reconstruction of the CT images, wherein F can represent a fan angle of the X-ray beams (e.g., X-ray radiation beams 206). This mode is called a half scan reconstruction or segment reconstruction. In accordance with embodiments of the present disclosure, FIG. 11illustrates a redundancy of sampling involved in a complete 2n radians axial scan due to existence of conjugate sampling pairs of line integrals. Conjugate sampling pairs of line integrals can be defined as follows. For every ray joining the focal spot of X-ray tube 402 at any detector channel of angle y, at a particular view angle, p, there exists another ray in the opposite direction, referred to as a conjugate ray, for a 2n radians axial scan. The conjugate ray can be obtained based on a view angle, [3conj =+ TI + 2y, from a channel having an angle of -y. This phenomenon is further illustrated by non-limiting scan plane 1120 of FIG. 11.

[0077] FIG. 5 illustrates a block diagram of an example, non-limiting system 500 to generate CT images from sinogram data generated by a detector of a CT system in accordance with one or more embodiments described herein. Repetitive description of like elements and / or processes employed in respective embodiments is omitted for sake of brevity.

[0078] With continued reference to FIGs. 1 and 2, non-limiting system 500 and / or the components of non-limiting system 500 can be employed to use hardware and / or software to solve problems that are highly technical in nature (e.g., related to CT imaging, CT detectors, CT image generation algorithms, etc.), that are not abstract and that cannot be performed as a set of mental acts by a human. Further, some of the processes performed may be performed by specialized computers for carrying out defined tasks related to generating CT images from data collected by asymmetrically positioned CT system detector units. Non-limiting system 500 and / or components of non-limiting system 500 can be employed to solve new problems that can arise through advancements in technologies mentioned above and / or the like. Non-limiting system 500 can provide technical improvements to CT imaging systems by improving a temporal resolution, spectral resolution and / or spatial resolution of CT images generated by CT imaging systems, reducing scan times (mm / s) and X-ray dosages (dose length product (DLP)) employed by CT imaging systems and increasing the life of hardware components such as X-ray tubes and X-ray detectors employed by CT imaging systems.

[0079] Non-limiting system 500 can comprise system 502. In various embodiments, system 502 can be operatively coupled to gantry 102 of non-limiting CT system 200. For example, system 502 can be part of computing device 216 or system 502 can be a separate system coupled to gantry 102 to generate CT images based on data collected by detector 208. Discussion turns briefly to processor 504, memory 506 and bus 508 of system 502. For example, in one or more embodiments, the system 502 can comprise processor 504 (e.g., computer processing unit, microprocessor, classical processor, and / or like processor). In one or more embodiments, a component associated with system 502, as described herein with or without reference to the one or more figures of the one or more embodiments, can comprise one or more computer and / or machine readable, writable and / or executable components and / or instructions that can beexecuted by processor 504 to enable performance of one or more processes defined by such component(s) and / or instruction(s). In one or more embodiments, system 502 can comprise a computer-readable memory (e.g., memory 506) that can be operably connected to the processor 504. Memory 506 can store computer-executable instructions that, upon execution by processor 504, can cause processor 504 and / or one or more other components of system 502 (e.g., image generation algorithm 510) to perform one or more actions. In one or more embodiments, memory 506 can store computer-executable components (e.g., image generation algorithm 510). System 502 and / or a component thereof as described herein, can be communicatively, electrically, operatively, optically and / or otherwise coupled to one another via bus 508. Bus 508 can comprise one or more of a memory bus, memory controller, peripheral bus, external bus, local bus, and / or another type of bus that can employ one or more bus architectures. One or more of these examples of bus 508 can be employed. In one or more embodiments, system 502 can be coupled (e.g., communicatively, electrically, operatively, optically and / or like function) to one or more external systems (e.g., a non-illustrated electrical output production system, one or more output targets, an output target controller and / or the like), sources and / or devices (e.g., classical computing devices, communication devices and / or like devices), such as via a network. In one or more embodiments, one or more of the components of system 502 can reside in the cloud, and / or can reside locally in a local computing environment (e.g., at a specified location(s)).

[0080] As discussed supra, system 502 can comprise one or more computer and / or machine readable, writable and / or executable components and / or instructions that, when executed by processor 504, can enable performance of one or more operations defined by such component(s) and / or instruction(s). For example, in various embodiments, image generation algorithm 510 can generate one or more CT images from X-rays (e.g., X-ray radiation beams 206) detected by detector 208 of a CT system (e.g., non-limiting CT system 100 or non-limiting CT system 200) by combining respective sinograms generated by respective detector units of detector 208, wherein the respective detector units can be asymmetrically positioned with respect to each other inside gantry 102 of the CT system to receive differentially sampled X-ray beams. The differentially sampled X-ray beams can enable detector 208 to capture more information for resolution-noise trade off and / or material properties about an entity being scanned (e.g., subject 106, entity 204, etc.), as compared to a conventional X-ray detector (e.g., non-limiting X-ray detector 300) that cannot detect differentially sampled X-ray beams due to symmetric positioning of detector units in the conventional X-ray detector. The respective detector units of detector 208 can generate respective sinograms based on the differentially sampled X-ray beams to extract clinically relevant information about an entity being scanned. The respective sinograms can be incomplete sinograms and image generation algorithm 510 can combine the incompletesinograms to generate completed sinograms. Image generation algorithm 510 can further employ the completed sinograms to reconstruct CT images.

[0081] In some embodiments, the combining of the respective sinograms can generate images with an enhanced spectral resolution, images capable of being material decomposed or a combination thereof to generate the one or more CT images for a defined X-ray dosage. Herein, the defined X-ray dosage can indicate an X-ray dosage equivalent to that employed by a CT system employing a conventional detector, such as non-limiting X-ray detector 300, for the same type of scan. In other embodiments, the combining can result in redundant measurements of line-integrals leading to improved noise characteristics in the one or more CT images at a defined scan coverage. Herein, the defined scan coverage can indicate a scan coverage equivalent to that utilized by a CT system employing a conventional detector, such as non-limiting X-ray detector 300, for the same type of scan. Further, a line-integral is defined as the cumulative attenuation experienced by an X-ray while traveling through an object from the focal spot of an X-ray tube to a particular detector cell. It is to be appreciated that the combining can result in redundant measurements of line-integrals only when the respective X-ray beams received by the asymmetrically positioned detector units are not spectrally separated. As described with reference to FIG. 9, X-ray beams can be spatially and / or spectrally separated by employing different combinations of a pre-patient filter or a post-patient filter with an X-ray detector, wherein the X-ray detector can comprise asymmetrically arranged detector units with similar or different material compositions and similar or different detector cell geometries.

[0082] In various embodiments, the asymmetric positioning of the respective detector units can increase collimation during X-ray scanning inside the CT system, reduce a scan time of the X-ray scanning, and improve temporal resolution of the one or more CT images generated by image generation algorithm 510 for the defined X-ray dosage. In various embodiments, the asymmetric positioning of the respective detector units can reduce the defined X-ray dosage for a scan as compared to an X-ray dosage employed by a symmetric positioning of the respective detector units, such as that of non-limiting X-ray detector 300, for the scan, which can further reduce a rate of degradation of components of the CT system.

[0083] In some embodiments, detector 208 can be a hyper-collimation detector, and the respective detector units of detector 208 can comprise a first detector unit (e.g., detector subarray 602) and a second detector unit (e.g., detector subarray 604). The first detector unit can be located on one side of an axis passing through center of rotation 234 of gantry 102 and running parallel to gantry 102 (i.e., the Z-axis), and the second detector unit can be located on the opposite side of the axis and offset from the first detector unit along the axis. As illustrated in FIGs. 1 and 2, detector 208, and thereby, the first detector unit and the second detector unit, canbe located inside gantry 102 across X-ray source 104 of the CT system. The geometry of the hyper-collimation detector is explained in greater detail infra with reference to at least FIG. 6.

[0084] In other embodiments, detector 208 can be a dual-hyper collimation detector, and the respective detector units of detector 208 can comprise a first detector unit (e.g., detector subarrays 801) and a second detector unit. The first detector unit can be located on one side of an axis passing through center of rotation 234 of gantry 102 and running parallel to gantry 102 (i.e., the Z-axis), and the first detector unit can comprise a first detector region having a first material composition and a second detector region having a second material composition that can be different from the first material composition. The second detector unit can be located on the opposite side of the axis and offset from the first detector unit along the axis, and the second detector unit can comprise a third detector region having the first material composition and a fourth detector region having the second material composition. As illustrated in FIGs. 1 and 2, detector 208, and thereby, the first detector unit and the second detector unit can be located inside gantry 102 across X-ray source 104 of the CT system. The geometry of the dual hypercollimation detector is explained in greater detail infra with reference to at least FIG. 8. In various embodiments, the first detector unit and the second detector unit can comprise different respective material compositions, structural constructions and / or physical dimensions.

[0085] In various embodiments, the respective detector units can comprise a first set of detector cells having first dimensions and a second set of detector cells having second dimensions that can be larger than the first dimensions, wherein the first dimensions can cause the first set of detector cells to generate high-resolution CT images, the second dimensions can cause the second set of detector cells to generate high SNR CT images, and combining the data from high-resolution detector subarray and the data from high SNR detector subarray can result in high-resolution and high-SNR CT images. Further, the first set of detector cells can have a first DGE and the second set of detector cells can have a second DGE that can be different from the first DGE.

[0086] The embodiments described with reference to FIG. 5 and additional aspects of image generation algorithm 510 are described in greater detail infra.

[0087] FIG. 6 illustrates diagrams of example, non-limiting configurations 600 and 610 of an X-ray detector in a CT system in accordance with one or more embodiments described herein. Repetitive description of like elements and / or processes employed in respective embodiments is omitted for sake of brevity.

[0088] Non-limiting configuration 600 and non-limiting configuration 610 illustrate asymmetric offset configurations provided by the various embodiments herein for detector subarrays of an X-ray detector (e.g., detector 208) that can be employed in a CT system (e.g.,non-limiting CT system 100 and / or non-limiting CT system 200). In various embodiments, the asymmetric offset configurations illustrated by non-limiting configurations 600 and 610 can be fully overlapping, partially overlapping or non-overlapping and are referred to as hypercollimation arrangements of the detector subarrays of the X-ray detector. In this regard, nonlimiting configurations 600 and 610 described herein comprise an asymmetric arrangement of detector subarrays of the X-ray detector to form a hyper-collimation detector, contrary to the configuration of non-limiting X-ray detector 300.

[0089] More specifically, in various embodiments, a CT system (e.g., non-limiting CT system 100 and / or non-limiting CT system 200) can comprise a hyper-collimation detector (e.g., detector 208) that can be located inside gantry 102 of the CT system and across X-ray source 104 of the CT system. The hyper-collimation detector can comprise detector subarray 602 located on one side of an axis passing through center of rotation 234 of gantry 102 and running parallel to gantry 102. The hyper-collimation detector can further comprise detector subarray 604 located on the opposite side of the axis and offset from the first detector unit along the axis. It is to be appreciated that the terms “detector subarray(s)” and “detector unit(s)” are used interchangeably throughout this specification. In non-limiting configurations 600 and 610, the axis is illustrated by line 606 which is parallel to the Z-axis of the Cartesian coordinate plane referenced herein.

[0090] Stated differently, the X-ray detector can be split into detector subarray 602 and a detector subarray 604, and detector subarray 602 and detector subarray 604 can be positioned asymmetrically with respect to one another about the Z-axis, along line 606. That is, detector subarray 602 and detector subarray 604 can be at an offset with respect to each other along the Z- axis. For example, as illustrated by non-limiting configuration 600, detector subarray 602 can be offset from detector subarray 604 along the Z-axis, or detector subarray 604 can be offset from detector subarray 602 along the Z-axis. In various embodiments, detector subarrays 602 and 604 can further comprise detector cells 608 that can be arranged in grids spanning the Z-X plane of the Cartesian coordinate system referenced throughout this specification. In various embodiments, detector cells 608 can be arranged in M rows, such that each of the detector cells 608 in the M rows can have a width m in the Z-axis direction, and detector cells 608 can be further arranged in N columns, such that each of detector cells 608 in the N columns can have a length n in the X-axis direction, wherein M, N, tn and n can be positive numeric values. As such, each of detector subarray 602 and detector subarray 604 can comprise M x (N / 2) detector cells. The width m and the length n of a detector cell of detector cells 608 can be in millimeters (mm). In some embodiments, respective ones of detector cells 608 of the hyper-collimation detector can have the same size. In other embodiments, respective ones of detector cells 608 of the hypercollimation detector can have different sizes. Thus, it is to be appreciated that although detectorsubarray 602 and detector subarray 604 are illustrated as respectively comprising the same number of detector cells, in some embodiments, detector subarray 602 and detector subarray 604 can respectively comprise different numbers of cells, and the respective distal ends of detector subarray 602 and detector subarray 604 can also be at different distances along the X-axis from line 606.

[0091] In various embodiments, detector subarray 604 can be offset from detector subarray 602 along the Z-axis by a distance that is equal to an integer multiple of a width of a detector cell of the respective detector cells of detector cells 608, wherein the distance is a fixed value or is dynamically adjusted via electromechanical devices. For example, the offset between detector subarray 602 and detector subarray 604 can be equal to i x m (i.e., offset = i x m), wherein i can be an integer between 0 to M. Thus, i = 0 can correspond to a first configuration of detector subarrays 602 and 604, which first configuration can be similar to that of detector subarrays 306 and 308 of non-limiting X-ray detector 300 and can thereby correspond to an arrangement of detector subarrays without any offset between the detector subarrays. In other words, for i = 0, detector subarrays 602 and 604 can completely overlap in the Z-direction.

[0092] In various embodiments, detector subarray 602 and detector subarray 604 can also be adjustable to a partially overlapping configuration or non-overlapping configuration along the Z-axis by adjusting the distance by which detector subarray 602 and detector subarray 604 can be offset from each other along the axis. For example, i = M can correspond to a second configuration of detector subarrays 602 and 604 where detector subarray 602 and detector subarray 604 can have no overlap with respect to each other along the Z-axis, and a maximum offset, imax, can be achieved. Such a configuration refers to the non-overlapping configuration as illustrated by non-limiting configuration 610. In the non-overlapping configuration, the collimation per turn of gantry 102 can be effectively doubled by employing a pre-patient filter that can block X-rays from portions on gantry 102 where the X-ray detector is absent, for example, as compared to that achieved by a CT system employing a conventional X-ray detector, for an equivalent X-ray dosage. Thus, twice the number of CT images can be generated, and the scan time can be twice as fast as that achieved with a conventional X-ray detector for the same amount of X-ray dosage. For example, if one image can be generated for data sampled for each row of the X-ray detector, which image can be called the native sampling image, an X-ray detector with 2M rows, such as the X-ray detector having non-limiting configuration 610, can generate twice the number of images generated by an X-ray detector with M rows, such as nonlimiting X-ray detector 300, wherein M can be a positive integer. Despite changing the geometric configuration of the X-ray detector, the capability of the CT system to generate CT images of sufficient quality for an entity / region of interest of an entity being scanned such thatthe CT images can be employed to diagnose a medical condition based on the data collected from the entity, can remain intact.

[0093] In various embodiments, 0 < i < M can correspond to a third configuration of detector subarrays 602 and 604, where detector subarray 602 and detector subarray 604 can partially overlap with respect to each other, such that the extent of overlap between detector subarray 602 and detector subarray 604 can neither be a complete overlap nor a zero overlap. Such a configuration refers to the partially overlapping configuration as illustrated by nonlimiting configuration 600. In various embodiments, the overlap of detector subarrays 602 and 604 can refer to an overlap of the respective edges of detector subarray 602 and detector subarray 604 facing line 606 along the Z-axis. In various embodiments, the partially overlapping configuration can result in better noise characteristics, and the non-overlapping configuration can result in a higher scan coverage for CT images generated by the CT system.

[0094] The hyper-collimation arrangements of detector subarrays 602 and 604 illustrated in FIG. 6 can increase collimation during imaging in the CT system, increase a number of the CT images generated by the CT system, and reduce a scan time to generate the CT images, as compared to an X-ray detector comprising symmetrically arranged detector subarrays (i.e., detector units) that are not offset with respect to one another (e.g., non-limiting X-ray detector 300), for a defined X-ray dosage and a fixed scan range. Herein, the fixed scan range can refer to the range of scan along the Z-axis. Further, the defined X-ray dosage can refer to an equivalent X-ray dosage employed by the CT system when employing a conventional X-ray detector, such as non-limiting X-ray detector 300. For example, in various embodiments, any one of detector subarray 602 and detector subarray 604 can be steadily shifted along the Z-axis direction, to establish an offset between detector subarray 602 and detector subarray 604, resulting in a steady increase in the coverage per axial scan or the overall collimation of the CT system. In various embodiments, for an offset equal to i x m between detector subarray 602 and detector subarray 604, with 0 < i < M, the scan coverage per axial scan, also known as the effective collimation, can be increased to a value given by (((M - i) x m) + (2 x i x m)). For example, in non-limiting configuration 600, the total scan coverage along the Z-axis can be 3 x m. In various embodiments, for an offset equal to i x m between detector subarray 602 and detector subarray 604, with i = M, the scan coverage per axial scan can be increased by a value given by 2 x M x m, thereby doubling the collimation.

[0095] In various embodiments, for the configuration of the X-ray detector with i = 0, there exists redundant sampling due to existence of conjugate rays for every ray in a full scan involving a 2TT rotation of gantry 102, as described elsewhere herein. The phenomenon of redundant sampling due to the existence of conjugate rays has been described in greater detailwith reference to FIG. 11. Such a configuration can provide multiple measurements of the same line integral, in principle improving SNR. In various embodiments, for an offset = i x m, with 0 < i < M, there exists a redundant conjugate sampling for a scan coverage of ((M - z) x m) leading to better SNR due to multiple measurements of the line integral. For the remaining coverage of (2 x i x m), sufficient samples as needed according to the Nyquist sampling theorem exist for image reconstruction, with appropriate conjugate synthesis. Similarly, for an offset = i x m, with i = M, sufficient samples as needed according to the Nyquist sampling theory exist for image reconstruction, with appropriate conjugate synthesis. That is, non-limiting configuration 600 with 0 < i < M can correspond to a combination of the previous two cases (i.e., offsets with i = 0 and i = M), where some rows of detector cells 608 can have redundant samples and other rows do not have redundant samples. In non-limiting configuration with i = M, the total time taken to scan a subject for a distance L along the Z-axis, can be decreased by two times. This can further reduce artifacts associated with motion and breathing. In general, an increase in scan coverage can reduce the number of scans that need to be executed by the CT system to scan a region of the subject as compared to the number of scans that need to be executed by the CT system in case of a conventional detector. The increase in the scan coverage can further reduce usage of components such as X-ray tube 402 and detector 208 and increase the life of the components. In various embodiments, the hyper-collimation detector can be operable in / compatible with a step and shoot mode, a helical mode or a cine mode of the CT system.

[0096] In various embodiments, an electromechanical assembly can be employed to dynamically configure the geometry of the hyper-collimation detector. For example, detector subarrays 602 and 604 and respective motions of detector subarrays 602 and 604 can be controlled dynamically via electromechanical systems. In various embodiments, the hypercollimation detector can be mounted on the electromechanical assembly, and the geometry of the hyper-collimation detector can be dynamically configured prior to a scan, based on clinical factors and advantages associated with a configuration of the geometry of the hyper-collimation detector. For example, the configuration of detector subarray 602 and detector subarray 604 can be enabled by a static shift of either detector subarray 602 with respect to detector subarray 604, or by a static shift of either detector subarray 604 with respect to detector subarray 602.

[0097] With continued reference to FIG. 5, image generation algorithm 510 can be a computer-executable algorithm that can be employed by the CT system to reconstruct images from each of the asymmetric detector subarrays, detector subarray 602 and detector subarray 604. For example, image generation algorithm 510 can complete the respective sinograms generated by detector subarray 602 and detector subarray 604 for locations of the hyper-collimation detector with missing detector cells 608 corresponding to respective conjugate channels. Stateddifferently, image generation algorithm 510 can generate sinograms for regions of the X-ray detector devoid of detector cells 608, which regions can be located across line 606 from detector subarray 602 and detector subarray 604 and be symmetric to detector subarray 602 and detector subarray 604. In non-limiting configuration 610, one such region is illustrated by block 612 with the dashed lines. The existence of sufficient samples per the Nyquist sampling theorem, in an axial scan of 2n radians in the X-ray detector configurations proposed by embodiments of the present disclosure can ensure an acceptable / sufficient image quality of CT images for diagnosis. In various embodiments, the CT images can be reconstructed by image generation algorithm 510 from the completed sinograms using FBP.

[0098] FIG. 7 illustrates diagrams of example, non-limiting configurations 700, 710, 720 and 730 of a pre-patient collimator in accordance with one or more embodiments described herein. Repetitive description of like elements and / or processes employed in respective embodiments is omitted for sake of brevity.

[0099] With continued reference to FIG. 6, in various embodiments, the CT system can further comprise a pre-patient collimator having a shape that can be based on a geometry of the hyper-collimation detector to selectively expose active regions of the hyper-collimation detector to X-rays (e.g., X-ray radiation beams 206) emitted from X-ray source 104 of the CT system to generate the CT images. In this regard, non-limiting configuration 700, non-limiting configuration 710, non-limiting configuration 720 and non-limiting configuration 730 illustrate different geometrical apertures of the pre-patient collimator. Non-limiting configuration 700 can correspond to a conventional aperture with a limited dose control of the X-rays. In this regard, non-limiting configuration 700 can correspond to a configuration of the hyper-collimation detector having an offset equal to i X m between detector subarray 602 and detector subarray 604 with i = 0, and having 2M number of detector rows. Non- limiting configuration 710 of the pre- patient collimator can correspond to non-limiting configuration 600 of the hyper-collimation detector having an offset equal to i X m between detector subarray 602 and detector subarray 604 with 0 < i < M. Non-limiting configuration 720 and non-limiting configuration 730 of the pre- patient collimator can correspond to non- limiting configuration 610 of the hyper-collimation detector having an offset equal to i X m between detector subarray 602 and detector subarray 604 with i - M.

[0100] Non-limiting configurations 720 and 730 illustrate the aperture geometries for the pre-patient collimator with increased effective collimation over an axial scan generated by a rotation of 2n radians of gantry 102 for an equivalent X-ray dose that can be employed by a conventional collimator (e.g., having a configuration identical to non-limiting configuration 700), for example, in conjunction with a conventional X-ray detector such as non-limiting X-raydetector 300. In this regard, the conventional collimator can refer to a collimator having a geometry based on the design of non-limiting X-ray detector 300. As stated supra, the prepatient collimator can be designed based on the geometry of the hyper-collimation detector to block the X-rays (e.g., X-ray radiation beams 206) from reaching regions of the entity being imaged, which regions can also correspond to portions of the X-ray detector devoid of detector cells 608, when the X-rays are projected onto the entity during CT imaging. For example, the pre-patient collimation enabled by the pre -patient collimator geometries proposed by the various embodiments herein can ensure that the subject is exposed to an X-ray dose (in millisievert (msv)), D, during an axial scan with an offset between detector subarray 602 and detector subarray 604 corresponding to i = M, for an effective collimation of 2 X M X m. On the contrary, with a conventional aperture geometry for the pre-patient collimation, as also illustrated by non-limiting configuration 700, the subject can be exposed to an X-ray dosage, 2 X D for a collimation of 2 X M X m. Thus, in various embodiments, the X-ray dose can be reduced by up to about 50 percent (%) for collimation with the hyper-collimation detector arrangement, as compared to the X-ray dosage employed by a conventional detector arrangement for the same amount of scan coverage.

[0101] FIG. 8 illustrates diagrams of example, non-limiting configurations 800 and 810 of an X-ray detector in a CT system in accordance with one or more embodiments described herein. Repetitive description of like elements and / or processes employed in respective embodiments is omitted for sake of brevity.

[0102] Non-limiting configurations 800 and 810 illustrate one or more geometrical configurations of the X-ray detector disclosed by the various embodiments herein. In various embodiments, a geometrical configuration of the X-ray detector can comprise different detector regions with different respective material compositions, different respective structural constructions and / or different respective physical dimensions. The detector regions can be respectively arranged in a hyper-collimation detector arrangement, wherein the detector regions can be juxtaposed by laterally inverting the detector regions in a first detector unit of the X-ray detector with respect to the detector regions in a second detector unit of the X-ray detector. Thus, the X-ray detector can have a dual hyper-collimation configuration, and the X-ray detector can be referred to as a dual hyper-collimation detector.

[0103] More specifically, in various embodiments, a CT system (e.g., non-limiting CT system 100 and / or non-limiting CT system 200) can comprise a detector (e.g., detector 208) that can be a dual hyper-collimation detector located inside gantry 102 of the CT system and across X-ray source 104 of the CT system. In various embodiments, the dual hyper-collimation detector can comprise detector subarrays 801 located on one side of an axis passing through center ofrotation 234 of gantry 102 and running parallel to gantry 102, wherein detector subarrays 801 can comprise first detector region 802 having a first material composition and second detector region 804 having a second material composition that is different from the first material composition. The dual-hyper collimation detector can further comprise detector subarrays 805 located on the opposite side of the axis and offset from detector subarrays 801 along the axis, wherein detector subarrays 805 can comprise third detector region 806 having the first material composition and fourth detector region 808 having the second material composition. In non-limiting configurations 800 and 810, the axis is illustrated by line 807 which is parallel to the Z-axis of the Cartesian coordinate plane referenced herein. In various embodiments, an arrangement of third detector region 806 and fourth detector region 808 can be juxtaposed and laterally inverted with respect to first detector region 802 and second detector region 804, as illustrated by nonlimiting configurations 800 and 810. In this regard, the dual hyper-collimation detector can be equivalent to two hyper-collimation detectors wherein the first detector region 802 and the third detector region 806 can form the first hyper-collimation detector, and the second detector region 804 and the fourth detector region 808 can form the second hyper-collimation detector. In various embodiments, the dual hyper-collimation detector can be operable in / compatible with a step and shoot mode, a helical mode or a cine mode of the CT system to generate the CT images.

[0104] In some embodiments, first detector region 802, second detector region 804, third detector region 806 and fourth detector region 808 can have different respective material compositions, structural constructions and / or physical dimensions. In various embodiments, spectral properties of the first material composition can be identical to or different from spectral properties of the second material composition. In various embodiments, physical dimensions of first respective detector cells (or detector elements) comprised in first detector region 802 and third detector region 806 can be identical to or different from physical dimensions of second respective detectors cells (or detector elements) comprised in second detector region 804 and fourth detector region 808. For example, as discussed herein, the portions of detector subarrays 801 and 805 corresponding to first detector region 802 and third detector region 806 can vary in material composition as compared to the portions of detector subarrays 801 and 805 corresponding to second detector region 804 and fourth detector region 808. In this regard, the first material composition and the second material composition can either have different X-ray spectral properties, different channel dimensions, or a combination thereof. The different channel dimensions can lead to a varied resolution and / or DQE for the respective regions of the dual-hyper collimation detector.

[0105] With continued reference to FIG. 5, image generation algorithm 510 can be a computer-executable algorithm that can be employed to generate CT images / clinical images withenhanced image quality compared to that of CT images generated by a CT system employing a conventional detector such as non-limiting X-ray detector 300. For example, image generation algorithm can be a sinogram completion algorithm that can be employed by a CT system to extract a complete sinogram from respective ones of detector subarrays 801 and 805 arranged in the dual hyper-collimation configuration. Thereafter, FBP can be employed to generate the CT images from each of the detector subarrays. In various embodiments, the geometry of the dualhyper collimation detector can increase collimation during imaging in the CT system, increase a number of the CT images generated by the CT system, and reduce a scan time to generate the CT images, as compared to a conventional X-ray detector comprising symmetrically arranged detector subarrays (i.e., detector units) that are not offset with respect to each other (e.g., nonlimiting X-ray detector 300), for a defined X-ray dosage and a fixed scan range. In various embodiments, the geometry of the dual hyper-collimation detector can cause the dual hypercollimation detector to detect differentially sampled X-ray beams to generate a greater amount of spatial resolution information about an entity being imaged by the CT system, a greater amount of spectral separation information about the entity, or a combination thereof, as compared to of the respective types of information resulting from a conventional X-ray detector comprising symmetrically arranged detector subarrays (i.e., detector units) that are not offset with respect to each other (e.g., non-limiting X-ray detector 300), for a defined X-ray dosage and a fixed scan range. Herein, the fixed scan range can refer to the range of scan along the Z-axis. Further, the defined X-ray dosage can refer to an equivalent X-ray dosage employed by the CT system when employing a conventional X-ray detector, such as non-limiting X-ray detector 300.

[0106] In an embodiment where detector subarrays 801 and 805 illustrated in FIG. 8 can be composed of detector elements having different spectral properties, that is, where the first material composition and the second material composition can have different spectral properties, the data from detector subarrays 801 can be combined with the data from detector subarrays 805. For example, the CT data from first detector region 802 and second detector region 804 can be respectively combined with the CT data from fourth detector region 808 and third detector region 806. In other words, data from detector subarrays on opposite sides of line 807 can be combined to obtain material decomposition (MD) images. The MD images generated by the dual hypercollimation detector can be generated at half the acquisition time and half the X-ray dose as that employed by a rotate-rotate scan using a conventional detector such as non-limiting X-ray detector 300. The reduced acquisition time can further increase temporal resolution of the CT images generated by the CT system and decrease the number of scans needed to achieve the same spectral resolution that can be achieved via a rotate-rotate scan. As a result, the life of the system components of the CT system can also be prolonged.

[0107] In an embodiment where detector subarrays 801 and 805 can be composed of detector elements (or detector cells) having different physical dimensions, the CT data from detector subarrays 801 can be combined with the CT data from detector subarrays 805 to obtain higher-resolution images with higher SNR as compared to CT images generated by a CT system employing a conventional X-ray detector. For example, detector cells in detector subarrays 801 and 805 can be arranged in a grid spanning the Z-X plane of the Cartesian coordinate system referenced throughout this specification, and respective detector cells can have a width m in the Z-axis direction and a length n in the X-axis direction. The width m and the length n of a detector cell can be in millimeters (mm). In the embodiment where detector subarrays 801 and 805 can be composed of detector elements having different physical dimensions, the sinograms generated by detector subarrays having detector cells with lower values of m and n can be employed to reconstruct CT images with higher resolution. Further, the sinograms obtained from detector subarrays with higher values of m and n can be used to reconstruct CT images with higher SNRs. In some embodiments, detector subarrays 801 and 805 can be composed of detector elements having different physical dimensions such that detector subarrays 801 can comprise a set of detector elements having first dimensions (e.g., higher or lower values of m and n) and detector subarrays 805 can comprise a set of detector elements having second dimensions (e.g., higher or lower values of m and n) that are different from the first dimensions. In other embodiments, each of detector subarrays 801 and 805 can comprise a combination of detector elements having different physical dimensions, and any combination of the detector elements with different physical dimensions can be implemented.

[0108] Since the CT data from higher resolution detector subarrays and the CT data from higher SNR detector subarrays can be obtained from the same region of the entity / same entity, they can be combined with each other (e.g., via image generation algorithm 510) to generate high resolution, high SNR CT images for the entity. Doing so can further decrease stresses on X-ray tube 402 and improve the life of X-ray tube 402 by reducing exposure of the X-ray tube 402 to X-rays, since a relatively less X-ray dosage can be utilized to generate the high resolution, high SNR images, for example, as comparted to the X-ray dosage utilized by a CT system employing a conventional detector such as non-limiting X-ray detector 300 comprising detector cells having the same dimensions, for the same type of scan.

[0109] In various embodiments, an electromechanical assembly can be employed to dynamically configure the geometry of the dual hyper-collimation detector. For example, detector subarrays 801 and detector subarrays 805 and respective motions of detector subarrays 801 and 805 can be controlled dynamically via electromechanical systems. In various embodiments, the dual hyper-collimation detector can be mounted on the electromechanicalassembly, and the geometry of the dual hyper-collimation detector can be dynamically configured prior to a scan, based on clinical factors and advantages associated with a configuration of the geometry of the dual hyper-collimation detector. For example, the configuration of detector subarrays 801 and detector subarrays 805 can be enabled by a static shift of either detector subarrays 801 with respect to detector subarrays 805, or by a static shift of either detector subarrays 805 with respect to detector subarrays 801.

[0110] FIG. 9 illustrates diagrams of example, non-limiting configurations 900 and 910 of a pre-patient filter and a post patient filter in accordance with one or more embodiments described herein. Repetitive description of like elements and / or processes employed in respective embodiments is omitted for sake of brevity.

[0111] With continued reference to FIG. 8, in various embodiments, the dual hypercollimation detector can be employed in the CT system in conjunction with one or more filters that can enhance at least a spectral resolution of CT images generated by the CT system. Respective filters of the one or more filters can be composed of a single material or dual materials. In various embodiments, the one or more filters can comprise a pre-patient filter to enhance the spectral resolution of the CT images, a post-patient filter to enhance the spectral resolution and spatial resolution of the CT images, or a combination of the pre-patient filter and the post-patient filter to further enhance the spectral resolution and the spatial resolution of the CT images. Although pre-patient filters can mainly be employed to enhance the spectral resolution of the CT images, in some embodiments, post-patient filters with high resolution grids can be employed to enhance the spatial resolution of the CT images. Enhanced spatial resolution can allow for fine structure visualization of areas of interest, for example, in a subject’s anatomy or in inanimate objects.

[0112] A pre-patient filter can perform pre-filtration of X-ray beams by altering the characteristics of X-ray beams emitted from X-ray tube 402 prior to interaction of the X-ray beams with an entity (e.g., subject 106, entity 204, etc.) being scanned. A pre-patient filter can alter properties of the X-ray photons in the X-ray beams by selectively allowing photons to pass through the entity. A pre-patient filter can provide advantages in terms of the penetration of the X-ray photons by hardening the energy of the X-ray beams, thereby giving rise to a spectral separation at the side of the X-ray detector, with no change with respect to the entity being scanned or to the detector. Thus, for a particular X-ray detector, different outputs can be achieved by changing the characteristics of the X-ray beam energy. A pre-patient filter can be located directly after X-ray tube 402, inside gantry 102. In terms of the order of components, X- ray tube 402 can generate and emit the X-rays, a collimator can control the amount of the X-rays,and the pre-patient filter can be located between the collimator and X-ray tube 402. The prepatient filter can primarily modify the spectrum of the X-ray beams.

[0113] A post-patient filter can ingest X-rays emitted by X-ray tube 402 and attenuated by the material of the entity being scanned. For example, a post-patient filter can filter the attenuated X-rays before the attenuated X-rays can interact with the X-ray detector (front face of the X-ray detector), and the post-patient filter can change the spectral properties of the X-rays. The post-patient filter can be located on top of a scintillator, inside the X-ray detector on gantry 102, and the post-patient filter can form an integral part of the front sensing surface of the X-ray detector. Thus, to perform such post- filtration, the aperture of an X-ray detector can be adjusted to make it beam blocking. A post-patient filter can narrow the area spanned by an X-ray beam via a high-resolution grid, or the post-patient filter can change the spectrum of X-ray beams attenuated by an entity being scanned to generate a desirable differentiation of X-ray beam energy for the X-ray detector.

[0114] In various embodiments, the X-ray detector proposed by embodiments of the present disclosure can comprise asymmetrically positioned detector units that can be different from each other either in terms of geometry, material composition or both geometry and material composition. Such combinations of detector units can enhance spatial resolution and / or spectral separability with respect to an entity being imaged. Spatial resolution of a CT system refers to the capability of a CT system to resolve the structural properties of an entity being imaged, and spectral separability of the CT system refers to the capability of the CT system to distinguish between different material properties of the entity. A pre-patient filter can also be employed to further aid in spectral separation of the X-ray beams. In an embodiment, employing a pre-patient filter in conjunction with a dual-hyper collimation arrangement of the X-ray detector, wherein respective detector units of the X-ray detector comprise the same material composition but different detector cell geometries, can enhance spectral separability of the X-ray beams. In another embodiment, employing a dual hyper-collimation arrangement of the X-ray detector, wherein respective detector units comprise different material compositions, can also enhance spectral separability of the X-ray beams. In yet another embodiment, employing the pre-patient filter in conjunction with a dual-hyper collimation arrangement of the X-ray detector, wherein respective detector units of the X-ray detector comprise different material compositions and different detector cell geometries, can enhance both spatial separability and spectral separability of the X-ray beams.

[0115] FIG. 9 illustrates the pre-patient filter and post-patient filter. In this regard, nonlimiting configuration 900 can represent a pre-patient filter or a post-patient filter, and nonlimiting configuration 910 can also represent a pre-patient filter or a post-patient filter. Invarious embodiments, two filter materials can be arranged in a dual hyper-collimation configuration in the pre-patient filter or a post-patient filter. For example, as illustrated in nonlimiting configurations 900 and 910, the pre-patient filter or a post-patient filter can comprise filter material 902 and filter material 904 in a dual-hyper collimation configuration.

[0116] The pre-patient filter and / or the post-patient filter can be designed to selectively filter an X-ray beam (e.g., X-ray radiation beams 206) to change the spectral characteristics of the X-ray beam impinging on detector 208, to facilitate spectral imaging. Further, the set-up of the pre-patient and / or post-patient filter can be configured in the CT system prior to executing a scanning process or during the scanning process. In some embodiments, the X-ray detector in such set-ups can comprise subarrays where all the detector cells can have the same physical dimensions and where the first material composition and the second material composition can have the same spectral properties. In other embodiments, the X-ray detector can comprise subarrays that can have different respective material compositions, structural constructions and / or physical dimensions.

[0117] In various embodiments, image generation algorithm 510 can be a computerexecutable algorithm that can be employed to generate spectrally resolved CT images, from data collected by an X-ray detector such as non-limiting X-ray detector 300, in conjunction with a pre-patient filter and / or a post-patient filter arranged in dual hyper-collimation configurations. Herein, the data collected by the X-ray detector can refer to X-rays detected by the X-ray detector and / or sinograms generated based on the X-rays detected by the X-ray detector. The resultant signal generated by the X-ray detector can be equivalent to that generated by a dual hyper-collimation detector employing materials with two different spectral properties, as discussed previously, wherein sinograms from the two hyper-collimation detectors of the dual hyper-collimation detector can be combined to obtain material-decomposition images.

[0118] FIG. 10 illustrates diagrams of example, non-limiting configurations of a CT detector mounted on an electromechanical assembly in accordance with one or more embodiments described herein. Repetitive description of like elements and / or processes employed in respective embodiments is omitted for sake of brevity.

[0119] With continued reference to the embodiments of at least FIGs. 6 and 8, FIG. 10 illustrates an X-ray detector mounted on electromechanical assembly 1002. Although FIG. 10 illustrates the dual-hyper collimation detector illustrated in FIG. 8, the X-ray detector assembly can be arranged in a hyper-collimation arrangement or in a dual hyper-collimation arrangement. That is, the X-ray detector can be a hyper-collimation detector as illustrated in FIG. 6 or a dualhyper collimation detector as illustrated in FIG. 8. Further, electromechanical assembly 1002 illustrates a simple mechanism; however, the such mechanisms can comprise additional hardwarecomponents in practice to enable mounting of the X-ray detector and configuring the X-ray detector to different geometries.

[0120] As discussed supra, the dual hyper collimation detector can comprise regions having two different material compositions (e.g., the first material composition and the second material composition) with different respective material properties. In various embodiments, the offset between detector subarrays 801 and detector subarrays 805 along the Z-axis can be controlled via electromechanical assembly 1002. Further, for detector cells having a width m and a length nithe offset can be equal to i x m, wherein i can be an integer between 0 and M, for M number of rows and N number of columns of the X-ray detector. In various embodiments, the X- M ray detector can be dynamically configured by setting the offset to negative (-) — < i < positiveM(+) as illustrated in non-limiting configurations 1000 and 1010, by employing electromechanical assembly 1002.

[0121] For example, for i = 0, the X-ray detector can have a dual-hyper collimationM M configuration as illustrated in non- limiting configuration 1000, whereas for i = - — or i = +identical portions of the X-ray detector having the spectral resolution or spectral properties can align symmetrically about the ISO-line, and the X-ray detector can have a dual-hyper collimation configuration as illustrated in non-limiting configuration 1010. For example, first detector region 802 can align symmetrically with third detector region 806. Doing so can allow the X-ray detector to obtain differentially sampled X-ray CT measurements of conjugate samples and provide additional information about the entity at a scan converge of M X m, for example, similar to that of non-limiting X-ray detector 300.

[0122] In various embodiments, the X-ray dosage for an entity being scanned can be controlled by appropriately adjusting an aperture of a pre-patient collimator, such as the prepatient collimator illustrated in FIG. 7. As discussed elsewhere herein, non-limiting configurations 1000 and 1010 can be adjusted prior to every scan based on the needs of the scan and clinical advantages associated with the respective configurations. The advantages of the different configurations of the X-ray detectors have been described at least with reference to FIGs. 6 and 8.

[0123] FIG. 11 illustrates diagrams of example, non-limiting scan planes 1100, 1110 and 1120 with X-ray beams for redundant samples and conjugate samples in accordance with one or more embodiments described herein. Repetitive description of like elements and / or processes employed in respective embodiments is omitted for sake of brevity.

[0124] FIG. 11 illustrates a scan plane of a CT imaging system (e.g., non-limiting CT system 100 and / or non-limiting CT system 200) similar to the scan plane illustrated in FIG. 4. Achannel angle, y, can be defined as an angle formed between a line (e.g., line 406 in FIG. 4) extending from a focal spot of X-ray tube 402 to a detector cell of an array of detector 208 and a line (e.g., line 408 in FIG. 4) extending from the focal spot of X-ray tube 402 to the ISO-center of the CT imaging system. A projection angle or view angle, p, can be defined as an angle formed between a line (e.g., line 408 in FIG. 4) joining the focal spot of X-ray tube 402 to the ISO-center of the CT imaging system and the Y-axis. For every row of detector 208, a sample can be collected for all views for a complete 2JI radian rotation (i.e., a 360° rotation of gantry 102), and the sample can be termed as a sinogram of the CT imaging system. The sinogram can be utilized in FBP techniques to reconstruct CT images of a scanned object using an axial scan of 2?r radians. However, a rotation of only n + F radians of gantry 102 can be sufficient for reconstruction of the CT images, wherein F can represent a fan angle of the X-ray beams (e.g., X-ray radiation beams 206). This mode is called a short scan / half scan reconstruction or segment reconstruction.

[0125] The fan angle can be defined as the angle formed by an X-ray beam, such as X- ray radiation beam 206, in the plane of rotation of the gantry of a CT system. Thus, 7t + F radians can refer to a movement of gantry 102 for 7t radians (180°or half circle) + F (fan angle in radians or equivalent angle in degrees) about the Z-axis during scanning. For example, at a given instant, gantry 102 can be stationary prior to a scan, and X-ray source can be positioned on the positive (+) Y-axis of the unit circle. Thereafter, gantry 102 can be rotated for 180° + F for a single scan, and X-ray source 104 can travel to a location close to the negative (-) X-axis on the unit circle. The amount of data generated during a TT + F radians movement of X-ray source 104 can be sufficient to generate a scan and reconstruct CT images for the scan, without needing a full turn of gantry 102.

[0126] In this regard, FIG. 11 illustrates a redundancy of sampling involved in a complete 2n: radians axial scan due to existence of conjugate sampling pairs of line integrals. That is, an axial scan with a 2a radians or 360° rotation of gantry 102 can involve redundancy of sampling. For example, non-limiting scan plane 1100 illustrates a position of X-ray tube 402 corresponding to an angle / ? = 0°, and non-limiting scan plane 1110 illustrates a position of X-ray tube 402 corresponding to an angle of [3 = 168°. As evident from FIG. 1 1, for every ray joining focal spot 1102 of X-ray tube 402 at any detector channel of angle y, at a particular view angle , there exists another ray in the opposite direction, referred to as a conjugate ray, for a 2it radians axial scan, as illustrated by non-limiting scan plane 1120. The conjugate ray can be obtained based on a view angle, (3ccnj = / ? + n + 2y, from a channel having an angle of negative (-)y. Thus, with reference to non-limiting scan plane 1120, (3conj = ft + n + 2y = 0° +TT + 2 X (—6) = 180° - 12° = 168°. It is to be appreciated that focal spot 1102 (or X-ray tube focal spot) can be a pointlocated on an imaginary plane inside X-ray tube 402 from which the X-rays can emanate. X-ray tube 402 can comprise a physical plane on a rotating target or track, and the high-velocity electrons of the X-rays can hit a Tungsten target on the physical plane. Thereafter, the X-rays can project through a window from X-ray tube 402. The virtual plane comprising the focal spot can be located between the window and the physical position on the track. Thus, focal spot 1102 can be a point in space inside X-ray tube 402.

[0127] FIG. 12 illustrates a flow diagram of an example, non-limiting method 1200 to generate imaging data from a CT system by selectively exposing an X-ray detector of the CT system to X-rays in accordance with one or more embodiments described herein. Repetitive description of like elements and / or processes employed in respective embodiments is omitted for sake of brevity.

[0128] Non-limiting method 1200 illustrates a computer-implemented method to acquire CT imaging data from the X-ray detector presented by embodiments of the present disclosure, via a controller (e.g., control mechanism 228) having data processing capability.

[0129] Non-limiting method 1200 can comprise, at step 1202, rotating an X-ray source and the X-ray detector around a subject. In some embodiments, the subject can be a human or animal patient under examination or a part of the body of the patient under examination. In other embodiments, the subject can be an inanimate object, one or more manufactured parts, and / or foreign objects such as dental implants, stents, and / or contrast agents present within the body of a subject.

[0130] Non-limiting method 1200 can comprise, at step 1204, selectively exposing (via control mechanism 228) one or more detector subarrays to an X-ray beam. For example, control mechanism 228 can selectively expose the surface areas of one or more detector subarrays to the X-ray beam.

[0131] Non-limiting method 1200 can comprise, at step 1206, acquiring data (via control mechanism 228) from the X-ray detector. For example, control mechanism 228 can acquire imaging data from the X-ray detector for further processing. The X-ray detector can typically comprise a scintillator for converting X-rays to light energy and photodiodes for receiving the light energy from the scintillator and producing electrical signals therefrom. Alternately, the X- ray detector can comprise a direct conversion device that can convert X-ray beams directly to electrical signals. Typically, each scintillator of a scintillator array can convert X-rays to light energy, and the individual scintillators can discharge the light energy to a photodiode adjacent to the scintillator array. Each photodiode can detect the light energy and generate a corresponding electrical signal. The outputs of the photodiodes may be transmitted to control mechanism 228 having the data processing capability, for calibration and image reconstruction.

[0132] Non-limiting method 1200 can comprise, at step 1208, combining one or more sinograms generated by respective detector subarrays to form a 3D image stack. For example, the sinograms generated by respective detector subarrays of the X-ray detector can be combined by control mechanism 228 to obtain a 3D image stack.

[0133] FIG. 13 illustrates flow diagrams of example, non-limiting methods 1300, 1310 and 1320 to generate CT images by employing a CT system in accordance with one or more embodiments described herein. Repetitive description of like elements and / or processes employed in respective embodiments is omitted for sake of brevity.

[0134] With continued reference to FIG. 12, non-limiting method 1300 illustrates an exemplary computer-implemented method to expose one or more detector subarrays / one or more areas of detector subarrays of the X-ray detector to an X-ray beam generated by the X-ray source. Non-limiting method 1300 can be an exemplary computer-implemented method to control X-ray exposure of a subject in conjunction with the cradle motion during CT imaging.

[0135] Non-limiting method 1300 can comprise, at step 1302, switching ON the X-ray source for a complete rotation of gantry 102.

[0136] Non-limiting method 1300 can comprise, at step 1304, switching OFF the X-ray source and shifting a patient cradle or bed of the CT system (e.g., table 108) based on collimation, along a Z-direction of the Cartesian coordinate system referenced herein, of the X- ray detector.

[0137] With continued reference to FIG. 12, non-limiting method 1310 illustrates another exemplary computer-implemented method to expose one or more detector subarrays / one or more areas of detector subarrays of the X-ray detector to an X-ray beam generated by the X-ray source. Non- limiting method 1310 can be an exemplary computer-implemented method to turn on X-ray emission and acquire data from an X-ray detector while the cradle is in a locked state during CT imaging.

[0138] Non-limiting method 1310 can comprise, at step 1312, locking the patient cradle and switching on the X-ray source for one or more rotations of gantry 102.

[0139] With continued reference to FIG. 12, non-limiting method 1320 illustrates yet another exemplary computer-implemented method to expose one or more detector subarrays / one or more areas of detector subarrays of the X-ray detector to an X-ray beam generated by the X- ray source. Non-limiting method 1320 can be an exemplary computer-implemented method to acquire data from an X-ray detector while the X-rays are being emitted and the cradle is moving at a constant velocity during CT imaging.

[0140] Non-limiting method 1320 can comprise, at step 1322, rotating gantry 102 at a first velocity according to a first pre-defined velocity profile and / or based on real-time feedback further based on data collected by the CT system.

[0141] Non-limiting method 1320 can comprise, at step 1324, moving the patient cradle through gantry 102 and along the Z-axis of the Cartesian coordinate system referenced herein, at a second velocity according to a second pre-defined velocity profile and / or based on real-time feedback further based on data collected by the CT system.

[0142] FIG. 14 illustrates a flow diagram of an example, non-limiting method 1400 to generate CT images by employing a CT system comprising a hyper-collimation detector in accordance with one or more embodiments described herein. Repetitive description of like elements and / or processes employed in respective embodiments is omitted for sake of brevity.

[0143] Non- limiting method 1400 can comprise, at 1402, generating CT images of an entity by employing a CT system comprising a hyper-collimation detector to differentially sample X-rays generated by an X-ray source of the CT system and attenuated by the entity, wherein the hyper-collimation detector comprises a first detector unit (e.g., detector subarray 602) located on one side of an axis passing through a center of rotation of a gantry of the CT system and running parallel to the gantry and a second detector unit (e.g., detector subarray 604) located on the opposite side of the axis and offset from the first detector unit along the axis, wherein the first detector unit and the second detector unit are also located inside the gantry and across the X-ray source.

[0144] Non-limiting method 1400 can comprise, at 1404, selectively exposing active regions of the hyper-collimation detector to the X-rays emitted from the X-ray source of the CT system by employing a pre-patient collimator, wherein the pre-patient collimator is designed according to a geometry of the hyper-collimation detector.

[0145] FIG. 15 illustrates a diagram of an example, non-limiting method 1500 to generate CT images by employing a CT system comprising a dual hyper-collimation detector in accordance with one or more embodiments described herein. Repetitive description of like elements and / or processes employed in respective embodiments is omitted for sake of brevity.

[0146] Non-limiting method 1500 can comprise, at 1502, generating CT images of an entity by employing a CT system comprising a dual hyper-collimation detector to differentially sample X-rays generated by an X-ray source of the CT system and attenuated by the entity, wherein the dual hyper-collimation detector comprises a first detector unit (e.g., detector subarrays 801) located on one side of an axis passing through a center of rotation of a gantry of the CT system and running parallel to the gantry, wherein the first detector unit comprises a first detector region having a first material composition and a second detector region having a secondmaterial composition that is different from the first material composition, and a second detector unit (e.g., detector subarrays 805) located on the opposite side of the axis and offset from the first detector unit along the axis, wherein the second detector unit comprises a third detector region having the first material composition and a fourth detector region having the second material composition.

[0147] FIG. 16 illustrates a diagram of an example, non-limiting method 1600 to generate CT images by employing an image generation algorithm in accordance with one or more embodiments described herein. Repetitive description of like elements and / or processes employed in respective embodiments is omitted for sake of brevity.

[0148] Non-limiting method 1600 can comprise, at 1602, generating, by a system operatively coupled to a processor, one or more CT images from X-rays detected by a detector of a CT system by combining respective sinograms generated by respective detector units of the detector, wherein the respective detector units are asymmetrically positioned with respect to each other inside a gantry of the CT system to receive differentially sampled X-ray beams.

[0149] Embodiments disclosed herein provide systems and methods that can comprise or be associated with an X-ray source configured to generate an X-ray beam, a detector arranged in a hyper-collimation configuration, comprising two subarrays that can be asymmetric with respect to a central axis and offset to each other in the Z-axis direction of the Cartesian coordinate system referenced herein, and a computer algorithm to generate images from X-ray data collected by the two subarrays and combining them to generate CT images. The systems and methods disclosed herein can allow for increased collimation, faster scan times, and improved temporal resolutions during CT imaging, while maintaining an X-ray dose similar to a system with a conventional detector (e.g., such as non-limiting X-ray detector 300). Further, the detector can be configured to be partially overlapping or non-overlapping by adjusting the offset between the two detector subarrays in the Z-axis direction. Further, the offset between the two detector subarrays may be fixed or configured dynamically by employing electromechanical devices. Further, a suitable pre-patient collimator is proposed to selectively expose only the active regions of the detector arranged in the hyper-collimation configuration to deliver an X-ray dose to a patient, equivalent to the X-ray dose delivered by the conventional detector, at a higher collimation. Further, a computer-implemented method is provided to reconstruct images from X-ray data collected by the two subarrays and combining them to generate CT images, which can provide higher collimation during CT imaging.

[0150] Embodiments disclosed herein provide systems and methods that can comprise or be associated with an X-ray source configured to generate an X-ray beam and a detector arranged in a dual hyper-collimation configuration. The detector in the dual hyper-collimationconfiguration can comprise two detectors in hyper-collimation arrangements (hyper-collimation configured detectors), which two detectors can be laterally inverted and juxtaposed with respect to each other, and which two detectors can be composed of materials with distinct properties to achieve a clinically improved CT image quality compared to a conventional detector (e.g., such as non- limiting X-ray detector 300). The systems and methods disclosed herein can further comprise a computer algorithm to generate images from the individual hyper-collimation configured detectors and combining the data to obtain images with enhanced image quality compared to images obtained from the conventional detector, at the same X-ray dose. Further, the materials employed in each of the two detectors in the hyper-collimation arrangements can have different spectral properties. Further, a computer- implemented algorithm can be employed to combine the data obtained from each of the two detectors in the hyper-collimation arrangements to achieve an enhanced spectral resolution capable of material-decomposition in clinical images, as compared to that achieved by a CT system employing the conventional detector, at an equivalent X-ray dose. Further, detector cells employed in each of the two detectors in the hyper-collimation arrangements can have different physical dimensions. Further, a computer-implemented algorithm can be employed to generate high-resolution images based on X-ray data from detector cells having smaller dimensions and images with high SNR based on X- ray data from detector cells having larger physical dimensions, and to combine the two sets of data to obtain images having high-resolution at high SNR, as compared to images generated via the conventional detector, at an equivalent X-ray dose.

[0151] Embodiments disclosed herein provide systems and methods that can comprise or be associated with an X-ray source configured to generate an X-ray beam and a pre-patient collimator or a post-patient collimator that can be arranged in a dual hyper-collimation arrangement and be composed of distinct materials, resulting in spectrally resolved measurements at an X-ray detector. The systems and methods can further comprise a computer algorithm to generate images from X-ray data collected by the X-ray detector receiving differentially sampled beams and combining them to generate material-decomposed images. Further, the systems and methods can extend the life of components, such as an X-ray tube and the X-ray detector, of a corresponding CT system, while enhancing image quality parameters such as spatial, spectral, or temporal resolution. Further, the X-ray detector and the pre-patient or post-patient collimators can be dynamically configured to achieve a higher scan coverage with an offset between left-hand side and right-hand side detector subarrays of the X-ray detector, or better noise characteristics without an offset between the left-hand side and right-hand side detector subarrays of the X-ray detector.

[0152] Embodiments disclosed herein provide a system, a method and a framework that can comprise or be associated with an X-ray source configured to generate an X-ray beam, a detector arranged in a dual hyper-collimation configuration and comprising two detectors in hyper-collimation arrangements (hyper-collimation configured detectors) that can be laterally inverted and juxtaposed with respect to each other, wherein the two detectors can be composed of materials with distinct properties to achieve a clinically improved image quality for CT images, as compared to CT images generated by a conventional detector (e.g., such as non-limiting X-ray detector 300). The detector arranged in the dual-hyper collimation configuration can be mounted on an electromechanical assembly to dynamically configure a geometry of the detector. The system, method and framework provided herein can further comprise a computer algorithm to generate images from different hyper-collimation detector settings, such that an enhanced image quality at twice the collimation can be obtained for CT images generated by the computer algorithm, or redundant measurements of line-integrals leading to improved noise can be obtained at lower scan coverage. Further, the electromechanical assembly can be employed to configure the detector geometry prior to each scan, based on a clinical need and advantages associated with the configuration of the detector.

[0153] Embodiments disclosed herein provide a computer-implemented method wherein one or more areas of the detector can be exposed to X-ray beams generated by an X-ray source. In an embodiment, the computer-implemented method can comprise switching the X-ray source ON to cause the X-ray source to emit X-ray beams for a complete rotation of a gantry, switching the X-ray source OFF to cause the X-ray source to stop the emission of the X-ray beams, and shifting a patient cradle based on collimation along the Z-axis direction of the detector / CT system, with reference to the Cartesian coordinate system referenced herein. Thereafter, the switching ON and switching OFF of the X-ray source can be repeated. In another embodiment, exposing the one or more areas of the detector to the X-ray beams generated by the X-ray source can further comprise locking the patient cradle and switching ON the X-ray source for one or more rotations of the gantry. In yet another embodiment, exposing the one or more areas of the detector to the X-ray beams generated by the X-ray source can further comprise rotating a gantry of the CT system at a constant velocity and moving a patient cradle with a constant velocity along the Z-axis direction.

[0154] For simplicity of explanation, the computer-implemented and non-computer- implemented methodologies provided herein are depicted and / or described as a series of acts. It is to be understood that the subject innovation is not limited by the acts illustrated and / or by the order of acts, for example acts can occur in one or more orders and / or concurrently, and with other acts not presented and described herein. Furthermore, not all illustrated acts can be utilizedto implement the computer-implemented and non-computer-implemented methodologies in accordance with the described subject matter. Additionally, the computer-implemented methodologies described hereinafter and throughout this specification are capable of being stored on an article of manufacture to enable transporting and transferring the computer-implemented methodologies to computers. The term article of manufacture, as used herein, is intended to encompass a computer program accessible from any computer-readable device or storage media.

[0155] The systems and / or devices have been (and / or will be further) described herein with respect to interaction between one or more components. Such systems and / or components can include those components or sub-components specified therein, one or more of the specified components and / or sub-components, and / or additional components. Sub-components can be implemented as components communicatively coupled to other components rather than included within parent components. One or more components and / or sub-components can be combined into a single component providing aggregate functionality. The components can interact with one or more other components not specifically described herein for the sake of brevity, but known by those of skill in the art.

[0156] In order to provide additional context for various embodiments described herein, FIG. 17 and the following discussion are intended to provide a brief, general description of a suitable computing environment 1700 in which the various embodiments described herein can be implemented. While the embodiments have been described above in the general context of computer-executable instructions that can run on one or more computers, those skilled in the art will recognize that the embodiments can be also implemented in combination with other program modules or as a combination of hardware and software.

[0157] Generally, program modules include routines, programs, components, data structures, etc., that perform particular tasks or implement particular abstract data types. Moreover, those skilled in the art will appreciate that the inventive methods can be practiced with other computer system configurations, including single-processor or multi-processor computer systems, minicomputers, mainframe computers, Internet of Things (loT) devices, distributed computing systems, as well as personal computers, hand-held computing devices, microprocessor-based or programmable consumer electronics, and the like, each of which can be operatively coupled to one or more associated devices.

[0158] The illustrated embodiments of the embodiments herein can be also practiced in distributed computing environments where certain tasks are performed by remote processing devices that are linked through a communications network. In a distributed computing environment, program modules can be located in both local and remote memory storage devices.

[0159] Computing devices typically include a variety of media, which can include computer-readable storage media, machine-readable storage media, or communications media, which two terms are used herein differently from one another as follows. Computer-readable storage media or machine-readable storage media can be any available storage media that can be accessed by the computer and includes both volatile and nonvolatile media, removable and nonremovable media. By way of example, and not limitation, computer-readable storage media or machine-readable storage media can be implemented in connection with any method or technology for storage of information such as computer-readable or machine-readable instructions, program modules, structured data or unstructured data.

[0160] Computer-readable storage media can include, but are not limited to, random access memory (RAM), read only memory (ROM), electrically erasable programmable read only memory (EEPROM), flash memory or other memory technology, compact disk read only memory (CD-ROM), digital versatile disk (DVD), Blu-ray disc (BD) or other optical disk storage, magnetic cassettes, magnetic tape, magnetic disk storage or other magnetic storage devices, solid state drives or other solid state storage devices, or other tangible or non-transitory media which can be used to store desired information. In this regard, the terms “tangible” or “non-transitory” herein as applied to storage, memory or computer-readable media, are to be understood to exclude only propagating transitory signals per se as modifiers and do not relinquish rights to all standard storage, memory or computer-readable media that are not only propagating transitory signals per se.

[0161] Computer-readable storage media can he accessed by one or more local or remote computing devices, e.g., via access requests, queries or other data retrieval protocols, for a variety of operations with respect to the information stored by the medium.

[0162] Communications media typically embody computer-readable instructions, data structures, program modules or other structured or unstructured data in a data signal such as a modulated data signal, e.g., a carrier wave or other transport mechanism, and includes any information delivery or transport media. The term “modulated data signal” or signals refers to a signal that has one or more of its characteristics set or changed in such a manner as to encode information in one or more signals. By way of example, and not limitation, communication media include wired media, such as a wired network or direct-wired connection, and wireless media such as acoustic, RF, infrared and other wireless media.

[0163] With reference again to FIG. 17, the example environment 1700 for implementing various embodiments of the aspects described herein includes a computer 1702, the computer 1702 including a processing unit 1704, a system memory 1706 and a system bus 1708. The system bus 1708 couples system components including, but not limited to, the system memory1706 to the processing unit 1704. The processing unit 1704 can be any of various commercially available processors. Dual microprocessors and other multi-processor architectures can also be employed as the processing unit 1704.

[0164] The system bus 1708 can be any of several types of bus structure that can further interconnect to a memory bus (with or without a memory controller), a peripheral bus, and a local bus using any of a variety of commercially available bus architectures. The system memory 1706 includes ROM 1710 and RAM 1712. A basic input / output system (BIOS) can be stored in a non-volatile memory such as ROM, erasable programmable read only memory (EPROM), EEPROM, which BIOS contains the basic routines that help to transfer information between elements within the computer 1702, such as during startup. The RAM 1712 can also include a high-speed RAM such as static RAM for caching data.

[0165] The computer 1702 further includes an internal hard disk drive (HDD) 1714 (e.g., EIDE, SATA), one or more external storage devices 1716 (e.g., a magnetic floppy disk drive (FDD) 1716, a memory stick or flash drive reader, a memory card reader, etc.) and a drive 1720, e.g., such as a solid state drive, an optical disk drive, which can read or write from a disk 1722, such as a CD-ROM disc, a DVD, a BD, etc. Alternatively, where a solid state drive is involved, disk 1722 would not be included, unless separate. While the internal HDD 1714 is illustrated as located within the computer 1702, the internal HDD 1714 can also be configured for external use in a suitable chassis (not shown). Additionally, while not shown in environment 1700, a solid state drive (SSD) could be used in addition to, or in place of, an HDD 1714. The HDD 1714, external storage device(s) 1716 and drive 1720 can be connected to the system bus 1708 by an HDD interface 1724, an external storage interface 1726 and a drive interface 1728, respectively. The interface 1724 for external drive implementations can include at least one or both of Universal Serial Bus (USB) and Institute of Electrical and Electronics Engineers (IEEE) 1394 interface technologies. Other external drive connection technologies are within contemplation of the embodiments described herein.

[0166] The drives and their associated computer-readable storage media provide nonvolatile storage of data, data structures, computer-executable instructions, and so forth. For the computer 1702, the drives and storage media accommodate the storage of any data in a suitable digital format. Although the description of computer-readable storage media above refers to respective types of storage devices, it should be appreciated by those skilled in the art that other types of storage media which are readable by a computer, whether presently existing or developed in the future, could also be used in the example operating environment, and further, that any such storage media can contain computer-executable instructions for performing the methods described herein.

[0167] A number of program modules can be stored in the drives and RAM 1712, including an operating system 1730, one or more application programs 1732, other program modules 1734 and program data 1736. All or portions of the operating system, applications, modules, or data can also be cached in the RAM 1712. The systems and methods described herein can be implemented utilizing various commercially available operating systems or combinations of operating systems.

[0168] Computer 1702 can optionally comprise emulation technologies. For example, a hypervisor (not shown) or other intermediary can emulate a hardware environment for operating system 1730, and the emulated hardware can optionally be different from the hardware illustrated in FIG. 17. In such an embodiment, operating system 1730 can comprise one virtual machine (VM) of multiple VMs hosted at computer 1702. Furthermore, operating system 1730 can provide runtime environments, such as the Java runtime environment or the .NET framework, for applications 1732. Runtime environments are consistent execution environments that allow applications 1732 to run on any operating system that includes the runtime environment.Similarly, operating system 1730 can support containers, and applications 1732 can be in the form of containers, which are lightweight, standalone, executable packages of software that include, e.g., code, runtime, system tools, system libraries and settings for an application.

[0169] Further, computer 1702 can be enabled with a security module, such as a trusted processing module (TPM). For instance, with a TPM, boot components hash next in time boot components, and wait for a match of results to secured values, before loading a next boot component. This process can take place at any layer in the code execution stack of computer 1702, e.g., applied at the application execution level or at the OS kernel level, thereby enabling security at any level of code execution.

[0170] A user can enter commands and information into the computer 1702 through one or more wired / wireless input devices, e.g., a keyboard 1738, a touch screen 1740, and a pointing device, such as a mouse 1742. Other input devices (not shown) can include a microphone, an infrared (IR) remote control, a radio frequency (RF) remote control, or other remote control, a joystick, a virtual reality controller or virtual reality headset, a game pad, a stylus pen, an image input device, e.g., camera(s), a gesture sensor input device, a vision movement sensor input device, an emotion or facial detection device, a biometric input device, e.g., fingerprint or iris scanner, or the like. These and other input devices are often connected to the processing unit 1704 through an input device interface 1744 that can be coupled to the system bus 1708, but can be connected by other interfaces, such as a parallel port, an IEEE 1394 serial port, a game port, a USB port, an IR interface, a BLUETOOTH® interface, etc.

[0171] A monitor 1746 or other type of display device can be also connected to the system bus 1708 via an interface, such as a video adapter 1748. In addition to the monitor 1746, a computer typically includes other peripheral output devices (not shown), such as speakers, printers, etc.

[0172] The computer 1702 can operate in a networked environment using logical connections via wired or wireless communications to one or more remote computers, such as a remote computer(s) 1750. The remote computer(s) 1750 can be a workstation, a server computer, a router, a personal computer, portable computer, microprocessor-based entertainment appliance, a peer device or other common network node, and typically includes many or all of the elements described relative to the computer 1702, although, for purposes of brevity, only a memory / storage device 1752 is illustrated. The logical connections depicted include wired / wireless connectivity to a local area network (LAN) 1754 or larger networks, e.g., a wide area network (WAN) 1756. Such LAN and WAN networking environments are commonplace in offices and companies, and facilitate enterprise-wide computer networks, such as intranets, all of which can connect to a global communications network, e.g., the Internet.

[0173] When used in a LAN networking environment, the computer 1702 can be connected to the local network 1754 through a wired or wireless communication network interface or adapter 1758. The adapter 1758 can facilitate wired or wireless communication to the LAN 1754, which can also include a wireless access point (AP) disposed thereon for communicating with the adapter 1758 in a wireless mode.

[0174] When used in a WAN networking environment, the computer 1702 can include a modem 1760 or can be connected to a communications server on the WAN 1756 via other means for establishing communications over the WAN 1756, such as by way of the Internet. The modem 1760, which can be internal or external and a wired or wireless device, can be connected to the system bus 1708 via the input device interface 1744. In a networked environment, program modules depicted relative to the computer 1702 or portions thereof, can be stored in the remote memory / storage device 1752. It will be appreciated that the network connections shown are examples and other means of establishing a communications link between the computers can be used.

[0175] When used in either a LAN or WAN networking environment, the computer 1702 can access cloud storage systems or other network-based storage systems in addition to, or in place of, external storage devices 1716 as described above, such as but not limited to a network virtual machine providing one or more aspects of storage or processing of information. Generally, a connection between the computer 1702 and a cloud storage system can be established over a LAN 1754 or WAN 1756 e.g., by the adapter 1758 or modem 1760,respectively. Upon connecting the computer 1702 to an associated cloud storage system, the external storage interface 1726 can, with the aid of the adapter 1758 or modem 1760, manage storage provided by the cloud storage system as it would other types of external storage. For instance, the external storage interface 1726 can be configured to provide access to cloud storage sources as if those sources were physically connected to the computer 1702.

[0176] The computer 1702 can be operable to communicate with any wireless devices or entities operatively disposed in wireless communication, e.g., a printer, scanner, desktop or portable computer, portable data assistant, communications satellite, any piece of equipment or location associated with a wirelessly detectable tag (e.g., a kiosk, news stand, store shelf, etc.), and telephone. This can include Wireless Fidelity (Wi-Fi) and BLUETOOTH® wireless technologies. Thus, the communication can be a predefined structure as with a conventional network or simply an ad hoc communication between at least two devices.

[0177] FIG. 18 is a schematic block diagram of a sample computing environment 1800 with which the disclosed subject matter can interact. The sample computing environment 1800 includes one or more client(s) 1810. The client(s) 1810 can be hardware or software (e.g., threads, processes, computing devices). The sample computing environment 1800 also includes one or more server(s) 1830. The server(s) 1830 can also be hardware or software (e.g., threads, processes, computing devices). The servers 1830 can house threads to perform transformations by employing one or more embodiments as described herein, for example. One possible communication between a client 1810 and a server 1830 can be in the form of a data packet adapted to be transmitted between two or more computer processes. The sample computing environment 1800 includes a communication framework 1850 that can be employed to facilitate communications between the client(s) 1810 and the server(s) 1830. The client(s) 1810 are operably connected to one or more client data store(s) 1820 that can be employed to store information local to the client(s) 1810. Similarly, the server(s) 1830 are operably connected to one or more server data store(s) 1840 that can be employed to store information local to the servers 1830.

[0178] Various embodiments may be a system, a method, an apparatus or a computer program product at any possible technical detail level of integration. The computer program product can include a computer readable storage medium (or media) having computer readable program instructions thereon for causing a processor to carry out aspects of various embodiments. The computer readable storage medium can be a tangible device that can retain and store instructions for use by an instruction execution device. The computer readable storage medium can be, for example, but is not limited to, an electronic storage device, a magnetic storage device, an optical storage device, an electromagnetic storage device, a semiconductorstorage device, or any suitable combination of the foregoing. A non-exhaustive list of more specific examples of the computer readable storage medium can also include the following: a portable computer diskette, a hard disk, a random access memory (RAM), a read-only memory (ROM), an erasable programmable read-only memory (EPROM or Flash memory), a static random access memory (SRAM), a portable compact disc read-only memory (CD-ROM), a digital versatile disk (DVD), a memory stick, a floppy disk, a mechanically encoded device such as punch-cards or raised structures in a groove having instructions recorded thereon, and any suitable combination of the foregoing. A computer readable storage medium, as used herein, is not to be construed as being transitory signals per se, such as radio waves or other freely propagating electromagnetic waves, electromagnetic waves propagating through a waveguide or other transmission media (e.g., light pulses passing through a fiber-optic cable), or electrical signals transmitted through a wire.

[0179] Computer readable program instructions described herein can be downloaded to respective computing / processing devices from a computer readable storage medium or to an external computer or external storage device via a network, for example, the Internet, a local area network, a wide area network or a wireless network. The network can comprise copper transmission cables, optical transmission fibers, wireless transmission, routers, firewalls, switches, gateway computers or edge servers. A network adapter card or network interface in each computing / processing device receives computer readable program instructions from the network and forwards the computer readable program instructions for storage in a computer readable storage medium within the respective computing / processing device. Computer readable program instructions for carrying out operations of various embodiments can be assembler instructions, instruction-set-architecture (ISA) instructions, machine instructions, machine dependent instructions, microcode, firmware instructions, state-setting data, configuration data for integrated circuitry, or either source code or object code written in any combination of one or more programming languages, including an object oriented programming language such as Smalltalk, C++, or the like, and procedural programming languages, such as the "C" programming language or similar programming languages. The computer readable program instructions can execute entirely on the user’s computer, partly on the user's computer, as a standalone software package, partly on the user's computer and partly on a remote computer or entirely on the remote computer or server. In the latter scenario, the remote computer can be connected to the user's computer through any type of network, including a local area network (LAN) or a wide area network (WAN), or the connection can be made to an external computer (for example, through the Internet using an Internet Service Provider). In some embodiments, electronic circuitry including, for example, programmable logic circuitry, field-programmablegate arrays (FPGA), or programmable logic arrays (PLA) can execute the computer readable program instructions by utilizing state information of the computer readable program instructions to personalize the electronic circuitry, in order to perform various aspects.

[0180] Various aspects are described herein with reference to flowchart illustrations or block diagrams of methods, apparatus (systems), and computer program products according to various embodiments. It will be understood that each block of the flowchart illustrations or block diagrams, and combinations of blocks in the flowchart illustrations or block diagrams, can be implemented by computer readable program instructions. These computer readable program instructions can be provided to a processor of a general purpose computer, special purpose computer, or other programmable data processing apparatus to produce a machine, such that the instructions, which execute via the processor of the computer or other programmable data processing apparatus, create means for implementing the functions / acts specified in the flowchart or block diagram block or blocks. These computer readable program instructions can also be stored in a computer readable storage medium that can direct a computer, a programmable data processing apparatus, or other devices to function in a particular manner, such that the computer readable storage medium having instructions stored therein comprises an article of manufacture including instructions which implement aspects of the function / act specified in the flowchart or block diagram block or blocks. The computer readable program instructions can also be loaded onto a computer, other programmable data processing apparatus, or other device to cause a series of operational acts to be performed on the computer, other programmable apparatus or other device to produce a computer implemented process, such that the instructions which execute on the computer, other programmable apparatus, or other device implement the functions / acts specified in the flowchart or block diagram block or blocks.

[0181] The flowcharts and block diagrams in the Figures illustrate the architecture, functionality, and operation of possible implementations of systems, methods, and computer program products according to various embodiments. In this regard, each block in the flowchart or block diagrams can represent a module, segment, or portion of instructions, which comprises one or more executable instructions for implementing the specified logical function(s). In some alternative implementations, the functions noted in the blocks can occur out of the order noted in the Figures. For example, two blocks shown in succession can, in fact, be executed substantially concurrently, or the blocks can sometimes be executed in the reverse order, depending upon the functionality involved. It will also be noted that each block of the block diagrams or flowchart illustration, and combinations of blocks in the block diagrams or flowchart illustration, can be implemented by special purpose hardware-based systems that perform the specified functions or acts or carry out combinations of special purpose hardware and computer instructions.

[0182] While the subject matter has been described above in the general context of computer-executable instructions of a computer program product that runs on a computer or computers, those skilled in the art will recognize that this disclosure also can or can be implemented in combination with other program modules. Generally, program modules include routines, programs, components, data structures, etc. that perform particular tasks or implement particular abstract data types. Moreover, those skilled in the art will appreciate that various aspects can be practiced with other computer system configurations, including single-processor or multiprocessor computer systems, mini-computing devices, mainframe computers, as well as computers, hand-held computing devices (e.g., PDA, phone), microprocessor-based or programmable consumer or industrial electronics, and the like. The illustrated aspects can also be practiced in distributed computing environments in which tasks are performed by remote processing devices that are linked through a communications network. However, some, if not all aspects of this disclosure can be practiced on stand-alone computers. In a distributed computing environment, program modules can be located in both local and remote memory storage devices.

[0183] As used in this application, the terms “component,” “system,” “platform,” “interface,” and the like, can refer to and / or can include a computer-related entity or an entity related to an operational machine with one or more specific functionalities. The entities disclosed herein can be either hardware, a combination of hardware and software, software, or software in execution. For example, a component can be, but may not be limited to being, a process running on a processor, a processor, an object, an executable, a thread of execution, a program, and / or a computer. By way of illustration, both an application running on a server and the server can be a component. One or more components can reside within a process and / or thread of execution and a component can be localized on one computer and / or distributed between two or more computers. In accordance with an aspect of the disclosure, respective components can execute from various computer readable media having various data structures stored thereon. The components can communicate via local and / or remote processes such as in accordance with a signal having one or more data packets / data sets (e.g., data from one component interacting with another component in a local system, distributed system, and / or across a network such as the Internet with other systems via the signal). In accordance with another aspect of the disclosure, a component can be an apparatus with specific functionality provided by mechanical parts operated by electric or electronic circuitry, which may be operated by a software or firmware application executed by a processor. In such a case, the processor can be internal or external to the apparatus and can execute at least a part of the software or firmware application. As yet another example, a component can be an apparatus that provides specific functionality through electronic components without mechanical parts, wherein the electronic components can include a processor or other means toexecute software or firmware that confers at least in part the functionality of the electronic components. In accordance with another aspect of the disclosure, a component can emulate an electronic component via a virtual machine, e.g., within a cloud computing system.

[0184] In addition, the term “or” may be intended to mean an inclusive “or” rather than an exclusive “or.” That is, unless specified otherwise, or clear from context, “X employs A or B” may be intended to mean any of the natural inclusive permutations. That is, if X employs A; X employs B; or X employs both A and B, then “X employs A or B” may be satisfied under any of the foregoing instances. Moreover, articles “a” and “an” as used in the subject specification and annexed drawings should generally be construed to mean “one or more” unless specified otherwise or clear from context to be directed to a singular form. As used herein, the terms “example” and / or “exemplary” are utilized to mean serving as an example, instance, or illustration and are intended to be non-limiting. For the avoidance of doubt, the subject matter disclosed herein may not be limited by such examples. In addition, any aspect or design described herein as an “example” and / or “exemplary” may not necessarily to be construed as preferred or advantageous over other aspects or designs, nor it may be meant to preclude equivalent exemplary structures and techniques known to those of ordinary skill in the art.

[0185] The herein disclosure describes non-limiting examples. For ease of description or explanation, various portions of the herein disclosure utilize the term “each,” “every,” or “all” when discussing various examples. Such usages of the term “each,” “every,” or “all” are nonlimiting. In other words, when the herein disclosure provides a description that is applied to “each,” “every,” or “all” of some particular object or component, it should be understood that this is a non-limiting example, and it should be further understood that, in various other examples, it can be the case that such description applies to fewer than “each,” “every,” or “all” of that particular object or component.

[0186] As it may be employed in the subject specification, the term “processor” can refer to substantially any computing processing unit or device comprising, but not limited to, singlecore processors; single-processors with software multithread execution capability'; multi -core processors; multi-core processors with software multithread execution capability; multi-core processors with hardware multithread technology; parallel platforms; and parallel platforms with distributed shared memory. Additionally, a processor can refer to an integrated circuit, an application specific integrated circuit (ASIC), a digital signal processor (DSP), a field programmable gate array (FPGA), a programmable logic controller (PLC), a complex programmable logic device (CPLD), a discrete gate or transistor logic, discrete hardware components, or any combination thereof designed to perform the functions described herein.Further, processors can exploit nano-scale architectures such as, but not limited to, molecular andquantum-dot based transistors, switches and gates, in order to optimize space usage or enhance performance of user equipment. A processor can also be implemented as a combination of computing processing units. In this disclosure, terms such as “store,” “storage,” “data store,” data storage,” “database,” and substantially any other information storage component relevant to operation and functionality of a component are utilized to refer to “memory components,” entities embodied in a “memory,” or components comprising a memory. It is to be appreciated that memory and / or memory components described herein can be either volatile memory or nonvolatile memory or can include both volatile and non-volatile memory. By way of illustration, and not limitation, non-volatile memory can include read only memory (ROM), programmable ROM (PROM), electrically programmable ROM (EPROM), electrically erasable ROM (EEPROM), flash memory, or non-volatile random-access memory (RAM) (e.g., ferroelectric RAM (FeRAM). Volatile memory can include RAM, which can act as external cache memory, for example. By way of illustration and not limitation, RAM may be available in many forms such as synchronous RAM (SRAM), dynamic RAM (DRAM), synchronous DRAM (SDRAM), double data rate SDRAM (DDR SDRAM), enhanced SDRAM (ESDRAM), Synchlink DRAM (SLDRAM), direct Rambus RAM (DRRAM), direct Rambus dynamic RAM (DRDRAM), and Rambus dynamic RAM (RDRAM). Additionally, the disclosed memory components of systems or computer-implemented methods herein are intended to include, without being limited to including, these and any other suitable types of memory.

[0187] What has been described above include mere examples of systems and computer- implemented methods. It is, of course, not possible to describe every conceivable combination of components or computer-implemented methods for purposes of describing this disclosure, but one of ordinary skill in the art can recognize that many further combinations and permutations of this disclosure are possible. Furthermore, to the extent that the terms “includes,” “has,” “possesses,” and the like are used in the detailed description, claims, appendices and drawings such terms are intended to be inclusive in a manner similar to the term “comprising” as “comprising” may be interpreted when employed as a transitional word in a claim. The descriptions of the various examples have been presented for purposes of illustration, but are not intended to be exhaustive or limited to the examples disclosed. Many modifications and variations can be apparent to those of ordinary skill in the art without departing from the scope and spirit of the described examples. The terminology used herein was chosen to best explain the principles of the examples, the practical application or technical improvement over technologies found in the marketplace, or to enable others of ordinary skill in the art to understand the examples disclosed herein.

[0188] This written description uses examples to disclose the invention, including the best mode, and to enable any person skilled in the art to practice the invention, including making and using any computing system or systems and performing any incorporated methods. The patentable scope of the invention may be defined by the claims, and may include other examples that occur to those skilled in the art. Such other examples are intended to be within the scope of the claims if they have structural elements that do not differ from the literal language of the claims, or if they include equivalent structural elements with insubstantial differences from the literal language of the claims.

[0189] Examples of the present disclosure shown in the drawings and described above are example examples only and are not intended to limit the scope of the appended claims, including any equivalents as included within the scope of the claims. Various modifications are possible and will be readily apparent to the skilled person in the art. It is intended that any combination of non-mutually exclusive features described herein are within the scope of the present invention. That is, features of the described examples can be combined with any appropriate aspect described above and optional features of any one aspect can be combined with any other appropriate aspect. Similarly, features set forth in dependent claims can be combined with non- mutually exclusive features of other dependent claims, particularly where the dependent claims depend on the same independent claim. Single claim dependencies may have been used as practice in some jurisdictions require them, but this should not be taken to mean that the features in the dependent claims are mutually exclusive.

[0190] Various non-limiting aspects of embodiments described herein are provided in the following clauses.

[0191] CLAUSE 1: A computed tomography (CT) system, comprising: a hypercollimation detector located inside a gantry of the CT system and across an X-ray source of the CT system, the hyper-collimation detector further comprising: a first detector unit located on one side of an axis passing through a center of rotation of the gantry and running parallel to the gantry; and a second detector unit located on the opposite side of the axis and offset from the first detector unit along the axis; and a pre-patient collimator having a shape that is based on a geometry of the hyper-collimation detector to selectively expose active regions of the hypercollimation detector to X-rays emitted from the X-ray source of the CT system to generate CT images.

[0192] CLAUSE 2: The CT system of any preceding clause, wherein respective detector cells of the hyper-collimation detector have the same size, and wherein the second detector unit is offset from the first detector unit along the axis by a distance that is equal to an integer multipleof a width of a detector cell of the respective detector cells, wherein the distance is a fixed value or is dynamically adjusted via electromechanical devices.

[0193] CLAUSE 3: The CT system of any preceding clause, wherein the first detector unit and the second detector unit are adjustable to a partially overlapping configuration or nonoverlapping configuration along the axis by adjusting the distance, and wherein the partially overlapping configuration results in better noise characteristics, and wherein the non-overlapping configuration results in a higher scan coverage.

[0194] CLAUSE 4: The CT system of any preceding clause, further comprising: an electromechanical assembly used to dynamically configure the geometry of the hyper-collimation detector, wherein the hyper-collimation detector is mounted on the electromechanical assembly, and wherein the geometry of the hyper-collimation detector is dynamically configured prior to a scan, based on clinical factors and advantages associated with a configuration of the geometry of the hyper-collimation detector.

[0195] CLAUSE 5: The CT system of any preceding clause, wherein the hypercollimation detector is operable in a step and shoot mode, a helical mode or in a cine mode.

[0196] CLAUSE 6: The CT system of any preceding clause, wherein the geometry of the hyper-collimation detector increases collimation in the CT system, increases a number of the CT images generated and reduces scan time to generate the CT images, as compared to an X-ray detector wherein the first detector unit and the second detector unit are not offset with respect to one another along the axis, for a defined X-ray dosage and a fixed scan range.

[0197] CLAUSE 7: The CT system of clause 1 above with any set of combinations of clauses 2 - 6 above.

[0198] CLAUSE 8: A method, comprising: generating CT images of an entity by employing a CT system comprising a hyper-collimation detector to differentially sample X-rays generated by an X-ray source of the CT system and attenuated by the entity, wherein the hypercollimation detector comprises a first detector unit located on one side of an axis passing through a center of rotation of a gantry of the CT system and running parallel to the gantry and a second detector unit located on the opposite side of the axis and offset from the first detector unit along the axis, wherein the first detector unit and the second detector unit are also located inside the gantry and across the X-ray source; and selectively exposing active regions of the hypercollimation detector to the X-rays emitted from the X-ray source of the CT system by employing a pre-patient collimator, wherein the pre-patient collimator is designed according to a geometry of the hyper-collimation detector.

[0199] CLAUSE 9: The method of any preceding clause, wherein the hyper-collimation detector is mounted on an electromechanical assembly, and wherein the geometry of the hyper-collimation detector is dynamically configured via the electromechanical assembly prior to a scan, based on clinical factors and advantages associated with a configuration of the geometry of the hyper-collimation detector.

[0200] CLAUSE 10: The method of clause 8 above with any combination of clauses 8 and 9 above.

[0201] CLAUSE 11: A CT system, comprising: a dual hyper-collimation detector located inside a gantry of the CT system and across an X-ray source of the CT system, the dual hypercollimation detector further comprising: a first detector unit located on one side of an axis passing through a center of rotation of the gantry and running parallel to the gantry, wherein the first detector unit comprises a first detector region having a first material composition and a second detector region having a second material composition that is different from the first material composition; and a second detector unit located on the opposite side of the axis and offset from the first detector unit along the axis, wherein the second detector unit comprises a third detector region having the first material composition and a fourth detector region having the second material composition.

[0202] CLAUSE 12: The CT system of any preceding clause, wherein an arrangement of the third detector region and the fourth detector region is juxtaposed and laterally inverted with respect to the first detector region and the second detector region.

[0203] CLAUSE 13: The CT system of any preceding clause, wherein spectral properties of the first material composition are identical to or different from spectral properties of the second material composition.

[0204] CLAUSE 14: The CT system of any preceding clause, wherein physical dimensions of a first sets of detector cells comprised in the first detector region and the third detector region are identical to or different from physical dimensions of a second set of detector cells comprised in the second detector region and the fourth detector region.

[0205] CLAUSE 15: The CT system of any preceding clause, further comprising: one or more filters that enhance at least a spectral resolution of CT images generated by the CT system, wherein respective filters of the one or more filters are composed of a single material or dual materials, and wherein the one or more filters comprise a pre-patient filter to enhance the at least a spectral resolution of the CT images, a post-patient filter to enhance the at least a spectral resolution and spatial resolution of the CT images, or a combination of the pre-patient filter and the post-patient filter to further enhance the at least a spectral resolution and the spatial resolution of the CT images.

[0206] CLAUSE 16: The CT system of any preceding clause, further comprising: an electromechanical assembly used to dynamically configure a geometry of the dual hyper-collimation detector, wherein the dual hyper-collimation detector is mounted on the electromechanical assembly, and wherein the geometry of the dual hyper-collimation detector is dynamically configured prior to a scan, based on clinical factors and advantages associated with a configuration of the geometry of the dual hyper-collimation detector.

[0207] CLAUSE 17: The CT system of any preceding clause, wherein the dual hypercollimation detector is operable in a step and shoot mode, a helical mode or in a cine mode to generate CT images, and wherein a geometry of the dual hyper-collimation detector causes the dual hyper-collimation detector to detect differentially sampled X-ray beams to generate a greater amount of at least one type of information selected from a group consisting of spatial resolution information about an entity being imaged by the CT system, spectral separation information about the entity, or a combination thereof, as compared to an amount of information resulting from an X-ray detector wherein the first detector unit and the second detector unit are not offset with respect to one another along the axis, for a defined X-ray dosage and a fixed scan range.

[0208] CLAUSE 18: The CT system of clause 11 above with any set of combinations of clauses 12 - 17 above.

[0209] CLAUSE 19: A method, comprising: generating CT images of an entity by employing a CT system comprising a dual hyper-collimation detector to differentially sample X- rays generated by an X-ray source of the CT system and attenuated by the entity, wherein the dual hyper-collimation detector comprises a first detector unit located on one side of an axis passing through a center of rotation of a gantry of the CT system and running parallel to the gantry, wherein the first detector unit comprises a first detector region having a first material composition and a second detector region having a second material composition that is different from the first material composition, and a second detector unit located on the opposite side of the axis and offset from the first detector unit along the axis, wherein the second detector unit comprises a third detector region having the first material composition and a fourth detector region having the second material composition.

[0210] CLAUSE 20: The method of any preceding clause, wherein the first detector unit and the second detector unit are also located inside the gantry and across the X-ray source, and wherein the third detector region and the fourth detector region are employed in an arrangement that is juxtaposed and laterally inverted with respect to the first detector region and the second detector region.

[0211] CLAUSE 21: The method of any preceding clause, wherein the CT system further comprises one or more filters, wherein respective filters of the one or more filters are composed of a single material or dual materials, and wherein the one or more filters comprise a pre-patient filter to enhance at least a spectral resolution of the CT images, a post-patient filter to enhancethe at least a spectral resolution and spatial resolution of the CT images, or a combination of the pre-patient filter and the post-patient filter to further enhance the at least a spectral resolution and the spatial resolution of the CT images.

[0212] CLAUSE 22: The method of clause 19 above with any combinations of clauses 20 and 21 above.

[0213] CLAUSE 23: A system, comprising: a processor that executes computerexecutable components stored in memory, wherein the computer-executable components comprise: an image generation algorithm that generates one or more CT images from X-rays detected by a detector of a CT system by combining respective sinograms generated by respective detector units of the detector, wherein the respective detector units are asymmetrically positioned with respect to each other inside a gantry of the CT system to receive differentially sampled X-ray beams.

[0214] CLAUSE 24: The system of any preceding clause, wherein the combining generates images with an enhanced spectral resolution, images capable of being material decomposed, or a combination thereof to generate the one or more CT images for a defined X-ray dosage.

[0215] CLAUSE 25: The system of any preceding clause, wherein the combining results in redundant measurements of line-integrals leading to improved noise characteristics in the one or more CT images at a defined scan coverage.

[0216] CLAUSE 26: The system of any preceding clause, wherein asymmetric positioning of the respective detector units increases collimation during X-ray scanning inside the CT system, reduces a scan time of the X-ray scanning, and improves temporal resolution of the one or more CT images generated by the image generation algorithm, as compared to a symmetric positioning of the respective detector units with respect to each another, for a defined X-ray dosage and a fixed scan range.

[0217] CLAUSE 27: The system of any preceding clause, wherein the asymmetric positioning of the respective detector units reduces an X-ray dosage needed by the CT system for a scan, as compared that needed by the CT system in case of the symmetric positioning of the respective detector units with respect to each another for the scan, resulting in a reduced rate of degradation of components of the CT system.

[0218] CLAUSE 28: The system of any preceding clause, wherein the respective detector units comprise a first set of detector cells having first dimensions and a first detector geometric efficiency and a second set of detector cells having second dimensions and a second detector geometric efficiency, wherein the second dimensions are larger than the first dimensions, wherein the first dimensions cause the first set of detector cells to generate high-resolution data, whereinthe second dimensions cause the second set of detector cells to generate high signal-to-noise ratio (SNR) data, and wherein combining the high-resolution data and the high SNR data results in high-resolution and high-SNR CT images.

[0219] CLAUSE 29: The system of any preceding clause, wherein the detector is a hypercollimation detector, wherein the respective detector units comprise a first detector unit located on one side of an axis passing through a center of rotation of the gantry and running parallel to the gantry, wherein the respective detector units further comprise a second detector unit located on the opposite side of the axis and offset from the first detector unit along the axis, and wherein the first detector unit and the second detector unit are located inside the gantry and across an X- ray source of the CT system.

[0220] CLAUSE 30: The system of any preceding clause, wherein the detector is a dualhyper collimation detector, wherein the respective detector units comprise a first detector unit located on one side of an axis passing through a center of rotation of the gantry and running parallel to the gantry, wherein the first detector unit comprises a first detector region having a first material composition and a second detector region having a second material composition that is different from the first material composition, wherein the respective detector units further comprise a second detector unit located on the opposite side of the axis and offset from the first detector unit along the axis, wherein the first detector unit and the second detector unit are located inside the gantry and across an X-ray source of the CT system, and wherein the second detector unit comprises a third detector region having the first material composition and a fourth detector region having the second material composition.

[0221] CLAUSE 31: The system of clause 23 above with any set of combinations of clauses 24 - 30 above.

[0222] CLAUSE 32: A computer-implemented method, comprising: generating, by a system operatively coupled to a processor, one or more CT images from X-rays detected by a detector of a CT system by combining respective sinograms generated by respective detector units of the detector, wherein the respective detector units are asymmetrically positioned with respect to each other inside a gantry of the CT system to receive differentially sampled X-ray beams.

[0223] CLAUSE 33: The computer-implemented method of any preceding clause, further comprising: generating, by the system, images with an enhanced spectral resolution, images capable of being material decomposed, or a combination thereof to generate the one or more CT images for a defined X-ray dosage.

[0224] CLAUSE 34: The computer-implemented method of any preceding clause, further comprising: generating, by the system, the one or more CT images with improved noisecharacteristics for a defined scan coverage based on redundant measurements of line-integrals resulting from the combining.

[0225] CLAUSE 35: The computer-implemented method of clause 32 above with any combinations of clauses 33 and 34 above.

[0226] CLAUSE 36: A computer program product to generate CT images, the computer program product comprising a non-transitory computer readable memory having program instructions embodied therewith, the program instructions executable by a processor to cause the processor to: generate one or more CT images from X-rays detected by a detector of a CT system by combining respective sinograms generated by respective detector units of the detector, wherein the respective detector units are asymmetrically positioned with respect to each other inside a gantry of the CT system to receive differentially sampled X-ray beams.

Claims

CLAIMSWhat is claimed is:

1. A computed tomography (CT) system, comprising: a hyper-collimation detector located inside a gantry of the CT system and across an X-ray source of the CT system, the hyper-collimation detector further comprising: a first detector unit located on one side of an axis passing through a center of rotation of the gantry and running parallel to the gantry; and a second detector unit located on the opposite side of the axis and offset from the first detector unit along the axis; and a pre-patient collimator having a shape that is based on a geometry of the hypercollimation detector to selectively expose active regions of the hyper-collimation detector to X- rays emitted from the X-ray source of the CT system to generate CT images.

2. The CT system of claim 1 , wherein respective detector cells of the hyper-collimation detector have the same size, and wherein the second detector unit is offset from the first detector unit along the axis by a distance that is equal to an integer multiple of a width of a detector cell of the respective detector cells, wherein the distance is a fixed value or is dynamically adjusted via electromechanical devices.

3. The CT system of claim 2, wherein the first detector unit and the second detector unit are adjustable to a partially overlapping configuration or non-overlapping configuration along the axis by adjusting the distance, and wherein the partially overlapping configuration results in better noise characteristics, and wherein the non-overlapping configuration results in a higher scan coverage.

4. The CT system of claim 1, further comprising: an electromechanical assembly used to dynamically configure the geometry of the hypercollimation detector, wherein the hyper-collimation detector is mounted on the electromechanical assembly, and wherein the geometry of the hyper-collimation detector is dynamically configured prior to a scan, based on clinical factors and advantages associated with a configuration of the geometry of the hyper-collimation detector.

5. The CT system of claim 1, wherein the hyper-collimation detector is operable in a step and shoot mode, a helical mode or in a cine mode.

6. The CT system of claim 1, wherein the geometry of the hyper-collimation detector increases collimation in the CT system, increases a number of the CT images generated and reduces scan time to generate the CT images, as compared to an X-ray detector wherein the first detector unit and the second detector unit are not offset with respect to one another along the axis, for a defined X-ray dosage and a fixed scan range.

7. A method, comprising: generating CT images of an entity by employing a CT system comprising a hypercollimation detector to differentially sample X-rays generated by an X-ray source of the CT system and attenuated by the entity, wherein the hyper-collimation detector comprises a first detector unit located on one side of an axis passing through a center of rotation of a gantry of the CT system and running parallel to the gantry and a second detector unit located on the opposite side of the axis and offset from the first detector unit along the axis, wherein the first detector unit and the second detector unit are also located inside the gantry and across the X-ray source; and selectively exposing active regions of the hyper-collimation detector to the X-rays emitted from the X-ray source of the CT system by employing a pre-patient collimator, wherein the prepatient collimator is designed according to a geometry of the hyper-collimation detector.

8. The method of claim 7, wherein the hyper-collimation detector is mounted on an electromechanical assembly, and wherein the geometry of the hyper-collimation detector is dynamically configured via the electromechanical assembly prior to a scan, based on clinical factors and advantages associated with a configuration of the geometry of the hyper-collimation detector.

9. A CT system, comprising: a dual hyper-collimation detector located inside a gantry of the CT system and across an X-ray source of the CT system, the dual hyper-collimation detector further comprising: a first detector unit located on one side of an axis passing through a center of rotation of the gantry and running parallel to the gantry, wherein the first detector unit comprises a first detector region having a first material composition and a second detector region having a second material composition that is different from the first material composition; and a second detector unit located on the opposite side of the axis and offset from the first detector unit along the axis, wherein the second detector unit comprises a third detector region having the first material composition and a fourth detector region having the second material composition.

10. The CT system of claim 9, wherein an arrangement of the third detector region and the fourth detector region is juxtaposed and laterally inverted with respect to the first detector region and the second detector region.

11. The CT system of claim 9, wherein spectral properties of the first material composition are identical to or different from spectral properties of the second material composition.

12. The CT system of claim 9, wherein physical dimensions of a first sets of detector cells comprised in the first detector region and the third detector region are identical to or different from physical dimensions of a second set of detector cells comprised in the second detector region and the fourth detector region.

13. The CT system of claim 9, further comprising: one or more filters that enhance at least a spectral resolution of CT images generated by the CT system, wherein respective filters of the one or more filters are composed of a single material or dual materials, and wherein the one or more filters comprise a pre-patient filter to enhance the at least a spectral resolution of the CT images, a post-patient filter to enhance the at least a spectral resolution and spatial resolution of the CT images, or a combination of the prepatient filter and the post-patient filter to further enhance the at least a spectral resolution and the spatial resolution of the CT images.

14. The CT system of claim 9, further comprising: an electromechanical assembly used to dynamically configure a geometry of the dual hyper-collimation detector, wherein the dual hyper-collimation detector is mounted on the electromechanical assembly, and wherein the geometry of the dual hyper-collimation detector is dynamically configured prior to a scan, based on clinical factors and advantages associated with a configuration of the geometry of the dual hyper-collimation detector.

15. The CT system of claim 9, wherein the dual hyper-collimation detector is operable in a step and shoot mode, a helical mode or in a cine mode to generate CT images, and wherein a geometry of the dual hyper-collimation detector causes the dual hyper-collimation detector to detect differentially sampled X-ray beams to generate a greater amount of at least one type of information selected from a group consisting of spatial resolution information about an entity being imaged by the CT system, spectral separation information about the entity, or a combination thereof, as compared to an amount of information resulting from an X-ray detector wherein the first detector unit and the second detector unit are not offset with respect to one another along the axis, for a defined X-ray dosage and a fixed scan range16. A method, comprising: generating CT images of an entity by employing a CT system comprising a dual hypercollimation detector to differentially sample X-rays generated by an X-ray source of the CT system and attenuated by the entity, wherein the dual hyper-collimation detector comprises a first detector unit located on one side of an axis passing through a center of rotation of a gantry of the CT system and running parallel to the gantry, wherein the first detector unit comprises a first detector region having a first material composition and a second detector region having a second material composition that is different from the first material composition, and a second detector unit located on the opposite side of the axis and offset from the first detector unit along the axis, wherein the second detector unit comprises a third detector region having the first material composition and a fourth detector region having the second material composition.

17. The method of claim 16, wherein the first detector unit and the second detector unit are also located inside the gantry and across the X-ray source, and wherein the third detector region and the fourth detector region are employed in an arrangement that is juxtaposed and laterally inverted with respect to the first detector region and the second detector region.

18. The method of claim 16, wherein the CT system further comprises one or more filters, wherein respective filters of the one or more filters are composed of a single material or dual materials, and wherein the one or more filters comprise a pre-patient filter to enhance at least a spectral resolution of the CT images, a post-patient filter to enhance the at least a spectral resolution and spatial resolution of the CT images, or a combination of the pre-patient filter and the post-patient filter to further enhance the at least a spectral resolution and the spatial resolution of the CT images.

19. A system, comprising: a processor that executes computer-executable components stored in memory, wherein the computer-executable components comprise: an image generation algorithm that generates one or more CT images from X-rays detected by a detector of a CT system by combining respective sinograms generated by respective detector units of the detector, wherein the respective detector units are asymmetrically positioned with respect to each other inside a gantry of the CT system to receive differentially sampled X-ray beams.

20. The system of claim 19, wherein the combining generates images with an enhanced spectral resolution, images capable of being material decomposed, or a combination thereof to generate the one or more CT images for a defined X-ray dosage.

21. The system of claim 19, wherein the combining results in redundant measurements of line-integrals leading to improved noise characteristics in the one or more CT images at a defined scan coverage.

22. The system of claim 19, wherein asymmetric positioning of the respective detector units increases collimation during X-ray scanning inside the CT system, reduces a scan time of the X- ray scanning, and improves temporal resolution of the one or more CT images generated by the image generation algorithm, as compared to a symmetric positioning of the respective detector units with respect to each another, for a defined X-ray dosage and a fixed scan range.

23. The system of claim 22, wherein the asymmetric positioning of the respective detector units reduces an X-ray dosage needed by the CT system for a scan, as compared that needed by the CT system in case of the symmetric positioning of the respective detector units with respect to each another for the scan, resulting in a reduced rate of degradation of components of the CT system.

24. The system of claim 19, wherein the respective detector units comprise a first set of detector cells having first dimensions and a first detector geometric efficiency and a second set of detector cells having second dimensions and a second detector geometric efficiency, wherein the second dimensions are larger than the first dimensions, wherein the first dimensions cause the first set of detector cells to generate high-resolution data, wherein the second dimensions cause the second set of detector cells to generate high signal-to-noise ratio (SNR) data, and wherein combining the high-resolution data and the high SNR data results in high-resolution and high- SNR CT images.

25. The system of claim 19, wherein the detector is a hyper-collimation detector, wherein the respective detector units comprise a first detector unit located on one side of an axis passing through a center of rotation of the gantry and running parallel to the gantry, wherein the respective detector units further comprise a second detector unit located on the opposite side of the axis and offset from the first detector unit along the axis, and wherein the first detector unit and the second detector unit are located inside the gantry and across an X-ray source of the CT system.

26. The system of claim 19, wherein the detector is a dual-hyper collimation detector, wherein the respective detector units comprise a first detector unit located on one side of an axis passing through a center of rotation of the gantry and running parallel to the gantry, wherein the first detector unit comprises a first detector region having a first material composition and a second detector region having a second material composition that is different from the first material composition, wherein the respective detector units further comprise a second detector unit located on the opposite side of the axis and offset from the first detector unit along the axis, wherein the first detector unit and the second detector unit are located inside the gantry and across an X-ray source of the CT system, and wherein the second detector unit comprises a third detector region having the first material composition and a fourth detector region having the second material composition.

27. A computer-implemented method, comprising: generating, by a system operatively coupled to a processor, one or more CT images fromX-rays detected by a detector of a CT system by combining respective sinograms generated by respective detector units of the detector, wherein the respective detector units are asymmetrically positioned with respect to each other inside a gantry of the CT system to receive differentially sampled X-ray beams.

28. The computer-implemented method of claim 27, further comprising: generating, by the system, images with an enhanced spectral resolution, images capable of being material decomposed, or a combination thereof to generate the one or more CT images for a defined X-ray dosage.

29. The computer-implemented method of claim 27, further comprising: generating, by the system, the one or more CT images with improved noise characteristics for a defined scan coverage based on redundant measurements of line-integrals resulting from the combining.

30. A computer program product to generate CT images, the computer program product comprising a non-transitory computer readable memory having program instructions embodied therewith, the program instructions executable by a processor to cause the processor to: generate one or more CT images from X-rays detected by a detector of a CT system by combining respective sinograms generated by respective detector units of the detector, wherein the respective detector units are asymmetrically positioned with respect to each other inside a gantry of the CT system to receive differentially sampled X-ray beams.

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