Description:CROSS-REFERENCE TO RELATED APPLICATIONS AND PRIORITY
The present application does not claim priority from any application.
FIELD OF THE INVENTION
The present application relates to medical imaging technology. Particularly, X-ray detector for CT scanning technology, and encompasses applications in healthcare diagnostics, industrial inspection, and scientific research.
BACKGROUND AND INTRODUCTION
The background information herein below relates to the present disclosure but is not necessarily prior art.
Computed tomography also known as a CT scan or CAT scan is a painless medical imaging scan. It is employed by healthcare providers to detect injuries, illnesses, or assess the effectiveness of treatments within the body. The word "tomography" in the CT scan derived from the Greek word "tomos," which means “slices or sections”. In conjunction, the purpose of a CT scan is to generate sections of images of organs to help the healthcare provider take a closer look at person’s body and look for concerns or abnormalities.
CT imaging plays a crucial role in medical diagnostics, industrial inspection, and various other fields requiring three-dimensional visualization of objects. Conventional CT scanners typically utilize X-ray radiation to generate cross-sectional images of the scanned object. However, exposure to ionizing radiation poses potential health risks, and traditional CT scanners have limitations in terms of image resolution and flexibility in imaging configurations.
The CT scan is essentially an X-ray study, where a series of rays are rotated around a specified body part, and computer-generated cross-sectional images are produced. The advantage of these tomographic images compared to conventional X-rays is that they contain detailed information of a specified area in cross-section, eliminating the superimposition of images, which provides a tremendous advantage over plain films. CT scans provide excellent clinicopathological correlation for a suspected illness
The CT imaging system comprises a plurality of cameras positioned at predetermined locations around the object to be scanned. The cameras are synchronized to capture images simultaneously or sequentially as the object rotates or moves relative to the camera array. Each camera may be equipped with appropriate optics and sensors to optimize image quality and resolution.
The captured images are then processed using computational algorithms to reconstruct a three-dimensional representation of the object. Various techniques such as filtered back projection, iterative reconstruction, and machine learning-based approaches may be employed to enhance image quality and reduce artifacts. The reconstructed volume data can be visualized and analyzed using software tools to extract relevant information.
However, the need for X-ray sources, initial capital expenditure high cost of maintenance, artefact generation, limited resolution, limited flexibility, environmental impact, makes the CT scan or CT imaging accessible only to a narrow range of healthcare facilities, research institutions, and industrial applications.
The prior art US8872116B2 discloses apparatus for multi-camera X-ray flat panel detector. The prior art discloses plurality of cameras arranged in an array, an energy conversion component for converting first radiation to second radiation at a lower energy detectable by the plurality of cameras, at least one computer for processing the signals from each of the plurality cameras, and at least one processor configured to combine signals to form at least one image. However, it does not diaclose the arrangement of the camaras, scintillator, lens and lead glass.
There is, therefore, felt a need to that mitigates the drawbacks mentioned hereinabove or at least provide a suitable alternative and give detailed information about the method of arrangement of cameras, scintillator and other things that make it for a CT scan.
The present invention provides a CT imaging system and method that overcomes the limitations of conventional CT scanners. Instead of utilizing X-ray radiation, the system employs an array of cameras positioned around the object of interest. These cameras capture a series of two-dimensional images from various angles, enabling the reconstruction of a high-resolution three-dimensional representation of the object using computational algorithms.
Thus, the present invention pertains to a novel system and method for performing CT-scans using an array of cameras, offering enhanced cost-effectiveness along with superior imaging capabilities (Fig. 1). By eliminating the need for expensive X-ray sources and associated components, the system significantly reduces both initial procurement costs and long-term operational expenses while maintaining high-quality imaging results.
Advantages of the Invention:
Reduced radiation exposure eliminates the need for ionizing radiation, making it safer for patients and operators.
Enhanced flexibility allows for customizable imaging configurations and easy adaptation to different object sizes and shapes.
Improved image quality and high-resolution imaging capabilities result in sharper and clearer three-dimensional reconstructions.
Cost-effectiveness leading to lower operational costs and maintenance requirements compared to traditional CT scanners.
OBJECTIVES
Some of the objects of the present disclosure, which at least one embodiment herein satisfies, are as follows:
An object of the present disclosure is to provide a X-ray detector.
Another object of the present disclosure is to provide scintillator for converting X-ray to visible light.
Still another object of the present disclosure is to provide a lead glass beneath the said scintillator for X-ray blocking.
Still another object of the present disclosure is to provide a composite sheet for blocking electromagnetic interface (EMI).
Yet another object of the present disclosure is to provide an array of CMO cameras arranged beneath scintillator such that the arrangement overlaps with the adjacent camera to obtain a seamless image.
Further, another object of the present disclosure is to provide a method for method of detecting the X-ray for a CT-scan comprising one or more number of steps.
Other objects and advantages of the present disclosure will be more apparent from the following description, which is not intended to limit the scope of the present disclosure.
SUMMARY OF THE INVENTION
The present application relates to a X-ray detector for CT-scan and a method of detecting X-ray for a CT-scan thereof.
An x-ray detector (100) for a CT-scan comprising a scintillator (101)for converting x-ray to visible light; a lead glass (102) beneath the said scintillator (101) for x-ray blocking; a composite sheet (103) for blocking EMI and an array of CMO cameras (104) arranged beneath the scintillator (101) wherein the arrangement overlaps with the adjacent CMO camera (104) to obtain a seamless image.
A method (200) of detecting the X-ray for a CT-scan comprising the steps of arrangement of the cameras (201), lead glass and scintillator; mechanical pre-sets of the camera (202); software level pre-sets of CMO camera (203); synchronization among sub-systems (204); communication of the CMO cameras with the computer (205); and processing of the images (206) such that all the images form as a single image in a plane.
BRIEF DESCRIPTION OF THE ACCOMPANYING DRAWING
The X-detector for CT-scan and a method of the present disclosure are now described with the help of the accompanying drawing, in which:
Figure 1 illustrates the conventional CT-Scan using flat panel detector and an array camera based X-Ray detector in accordance with the present disclosure;
Figure 2 illustrates the, the camera mounting orientation with 3 mounting holes in accordance with the present disclosure;
Figure 3 (a) illustrates the CMO camera mounting on rectangular block in accordance with the present disclosure;
Figure 3 (b) illustrates the rectangular block mounted on rail and CMO camera mounted on railin accordance with the present disclosure;
Figure 3(c) illustrates the rectangular block mounted on rail with CMO camera seen from sidewise in accordance with the present disclosure;
Figure 4 (a) illustrates the arrangement of cameras in rows and columns on a stack in accordance with the present disclosure;
Figure 4 (b) illustrates the parallel arrangement of cameras using rail and stack in accordance with the present disclosure;
Figure 5 (a) illustrates the detector arrangement with camera, lens, lead glass, scintillator sheet and Hylam sheetin accordance with the present disclosure;
Figure 5 (b) illustrates the composite sheet connected to the casing or chassis groundin accordance with the present disclosure;
Figure 5 (c) illustrates the composite sheet for blocking X-Ray, EMI and visible light in accordance with the present disclosure;
Figure 6 (a) and 6 (b) illustrates the mage stitching coordinate selection and stitching parameter selection in accordance with the present disclosure; and
Figure 7 (a) illustrates the image alignment with cross wire phantom in accordance with the present disclosure.
Figure 7 (b) illustrates the lead screw arrangement to move the detector in accordance with the present disclosure.
Figure 8 (a) illustrates the lead gray scale variations based on location of camera w.r.t to X-ray tube in accordance with the present disclosure.
Figure 8 (b) illustrates the obtain gray scale value from the individual images in accordance with the present disclosure.
Figure 9 (a) illustrates the comparison of conventional method with the method of the instant invention for communication in accordance with the present disclosure.
Figure 9 (b) illustrates the drag chain based communication in accordance with the present disclosure.
Figure 10 (a) illustrates the encoder feedback to trigger all the cameras in accordance with the present disclosure.
DETAILED DESCRIPTION
Embodiments, of the present disclosure, will now be described with reference to the accompanying drawings. Embodiments are provided so as to thoroughly and fully convey the scope of the present disclosure to the person skilled in the art. Numerous details are set forth, relating to specific components, and methods, to provide a complete understanding of embodiments of the present disclosure. It will be apparent to the person skilled in the art that the details provided in the embodiments should not be construed to limit the scope of the present disclosure. In some embodiments, well-known processes, well-known apparatus structures, and well-known techniques are not described in detail.
The terminology used, in the present disclosure, is only for the purpose of explaining a particular embodiment and such terminology shall not be considered to limit the scope of the present disclosure. As used in the present disclosure, the forms "a,” "an," and "the" may be intended to include the plural forms as well, unless the context clearly suggests otherwise. The terms "comprises," "comprising," “including,” and “having,” are open ended transitional phrases and therefore specify the presence of stated features, integers, steps, operations, elements, modules, units and/or components, but do not forbid the presence or addition of one or more other features, integers, steps, operations, elements, components, and/or groups thereof. The particular order of steps disclosed in the method and process of the present disclosure is not to be construed as necessarily requiring their performance as described or illustrated. It is also to be understood that additional or alternative steps may be employed.When an element is referred to as being "mounted on," “engaged to,” "connected to," or "coupled to" another element, it may be directly on, engaged, connected or coupled to the other element. As used herein, the term "and/or" includes any and all combinations of one or more of the associated listed elements.
The terms first, second, third, etc.,should not be construed to limit the scope of the present disclosure as the aforementioned terms may be only used to distinguish one element, component, region, layer or section from another component, region, layer or section. Terms such as first, second, third etc., when used herein do not imply a specific sequence or order unless clearly suggested by the present disclosure.Terms such as “inner,” “outer,” "beneath," "below," "lower," "above," "upper," and the like, may be used in the present disclosure to describe relationships between different elements as depicted from the figures.
Conventional X-ray detectors have been integral to CT scanning technology for decades, providing essential capabilities for medical imaging. Further, the conventional CT-scan use the flat panel detector (Fig. 1). In addition, they are associated with limitations such as ionizing radiation exposure, limited resolution, potential for image artifacts, and high equipment costs. These drawbacks have spurred ongoing research and development efforts to improve detector technology and explore alternative imaging modalities for CT scanning.
A non-limiting embodiment of the present disclosure is to provide a X-ray detector (100) for a CT-scan.
Scintillator plays a vital role in an X-ray detector for CT scanning by converting incoming X-ray photons into visible light photons, which can then be detected and converted into electrical signals. Its efficient conversion of X-ray energy into visible light enables the detection and visualization of anatomical structures during CT scanning, contributing to the generation of diagnostic images.
In an embodiment of the present invention, the X-ray detector (100) for CT scan comprises a scintillator (101) for converting X-ray to visible light.
Lead glass, also known as leaded glass or leaded crystal, is commonly used in X-ray detectors for CT scanning due to its ability to provide both structural support, protection of sensitive electronics, optical clarity, and radiation shielding.
In a related embodiment of the present iunvention, the X-ray detector (100) for CT scan comprises a lead glass (102) beneath the scinitillator (101) for blocking X-ray.
The composite sheet are found to play a crucial role in enhancing the functionality, durability, and performance of an X-ray detector for CT scanning. In addition, by providing structural support, radiation transparency, EMI shielding, thermal stability, weight reduction, and customizability, composite sheet contribute to the overall efficiency and reliability of CT imaging systems.
In a further related embodiment, the X-ray detector (100) for the CT-scan comprises a composite sheet (103) for blocking EMI.
The coordinated positioning of the scintillator and cameras within the X-ray detector assembly is essential for the efficient capture and conversion of X-ray photons into detectable signals for image reconstruction in CT scanning. Together, these components play a critical role in producing high-quality CT images that aid in the diagnosis and treatment of various medical conditions. In a further related embodiment, the X-ray detector (100) for the CT-scan comprises an array of CMO cameras (104) arranged beneath the scintillator (101) such that each image overlaps the subsequent image.
In an another embodiment of the present invention, the scintillator (101) and CMO cameras (104) are arranged in a same plane to form the image.
As exemplarily illustrated in Fig. 5 (a), the X-ray detector (100) comprises a scintillator (101) for converting X-ray to visible light; a lead glass (102) beneath the scintillator (101) for blocking X-ray; a composite sheet (103) for blocking EMI and an array of CMO cameras (104) arranged beneath the scintillator (101) such that each image overlaps the subsequent image.
In a further related embodiment of the present disclosure, the composite sheet (103) is placed between the lens (105) and CMO camera (104) and is further connected to the ground point of the electronics (106).
As exemplarily illustrated in Fig 5(b), the X-ray detector (100) comprises the composite sheet (103) placed between the lens (105) and CMO camera (104) and is further connected to the ground point of the electronics (106).
In a still further related embodiment of the instant invention as illustrated in Fig 5(c), the composite sheet (103) comprises of an aluminium sheet (103A), a lead sheet (103B) and a black out fabric (103C).
In a yet another related embodiment of the present invention as illustrated in Fig 5(b), the said aluminium sheet (103A) is connected to the electronics ground point (106), the lead sheet (103B) block X-ray and black out fabric (103C) reduce light coming from backside of the detector.
In a further related embodiment of the present invention as illustrated in the Fig. 3 (a), the plurality of the CMO cameras (104) are arranged equidistant from each other and are fastened to the rail (107) through plurality of screws (108).
In a other related embodimentof the present invention as illustrated in Fig 3 (b & c), CMO camera (104) is mounted in a rail (107) with polished surface and a groove inside such that there is minimum play between the rail (107) and rectangular block for mounting the CMO camera (104).
In another embodiment of the instant invention, a method (100) of creating back projection image slices for CT-scan is disclosed.
In one illustrative embodiment, in accordance with the present disclosure, a method (200) of creating back projection image slices of present invention includes the following steps:
an arrangement of CMO cameras(104), lead glass (102) and scintillator (101) (201);
mechanical pre-sets of the CMO camera (104) (202);
software pre-sets of the CMO camera (102) (203);
synchronization among sub-systems (204);
communication of CMO cameras (104) with the computer (205); and
processing of the images (206)
such that all images form a single image in a plane.
Further, in accordance with another related embodiment, the X-ray detector (100) for the CT-scan comprises the arrangement of CMO camera (104) comprising the step mounting of said CMO camera (104) on a polished surface with plurality of mounting holes (201A) as illustratd in Fig. 2 and Fig 4(a & b). The plurality of holes (201A) preferably are selected in the range of 3 to 10 and preferably a minimum of 3 mounting holes for the more stable and better alignment to the center.
In one embodiment of the method (200), the step (201B ) inclues placing a block on the rail (107) with groove for sliding, fixing and reduced offset, rotation and tilt in the images followed by the step (201C) of mounting the rails (107) perpendicular to the stack and parallel to adjacent rails (107) as illustratd in Fig. 3( a, b & C) and Fig 4(a & b). In one embodiment of the present invention, said arrangement is such that all the images are aligned without rotation, offset or tilt.
In accordance with another embodiment of the method (200) as illustratd in Fig 6 (a & b), the step of the image stitching comprises the steps of set tile configuration, image coordinate selection, image stitching parameter setting and projection image file setting.
In yet another embodiment of the method (200), at a step (202), the the mechanical pre-sets are carried out by cross-wire phantom to the center of X-ray image. The mechanical presets results in the alignment of X-Ry tube with X-ray detector center.
The software presence associated with CMOS cameras in an X-ray detector for CT scanning is essential for optimizing image acquisition, processing, and reconstruction to produce high-quality diagnostic images for clinical interpretation and patient care. In another embodiment of the method (200), at step (203) the software level pre-sets of the CMO cameras (104) for stitched image correction comprises offset, rotation, tilt and lens distortion correction.
In yet another embodiment of the method (200), at step (204) the the synchronization among sub-systems (204) and communication of camera with the computer system (205) as illustrated in Fig. 9 (a&b) and Fig. 10 is carried out by first sending it to volatile memory and then to permanent memory, such that images are not lost during communication. Synchronization among subsystems (204) and communication of CMO camera (205) results in the X-ray detector (100) for CT scanning are essential for achieving accurate and high-quality imaging outcomes. Precise timing synchronization, efficient data acquisition, and effective inter-subsystem communication contribute to the diagnostic utility of CT imaging, enabling clinicians to obtain detailed anatomical information for accurate diagnosis and treatment planning.
In yet another embodiment of the method (200) as illustrated in Fig. 8(a & b), at step (206) the processing of image comprises of performing flat field calibration for each image generated from camera and gray scale equalization for the entire stack of projection images.
The present disclosure is further described in light of the following examples which are set forth for illustration purpose only and not to be construed for limiting the scope of the disclosure.
TECHNICAL ADVANCEMENTS
The present disclosure described herein above has several technical advantages including, but not limited to, the realization of:
The embodiments herein and the various features and advantageous details thereof are explained with reference to the non-limiting embodiments in the above description. Descriptions of well-known components and processing techniques are omitted so as to not unnecessarily obscure the embodiments herein.
The invention of a CT-Scan using an array of cameras and the method threrof introduces several significant technical advancements over existing prior art in the field of medical imaging:
• Reduced radiation exposure by eliminating the need for ionizing radiation.
• Safer by reducing the potential health risks associated with radiation exposure for both patients and operators,
• Enhanced flexibility by the use of an array of cameras for a highly flexible imaging configuration that allows the imaging of objects of varying sizes, shapes, and orientations
• Offer greater versatility in medical diagnostics and other applications.
• Improved image quality by the system's ability to capture images from multiple perspectives leading to high-resolution three-dimensional reconstructions of the scanned object.
• Provides sharper and clearer images, leading to an accurate diagnoses and better treatment planning.
• Cost-effectiveness by eliminating the need for expensive X-ray sources and related components.
• Accessible to a broader range of healthcare facilities and research institutions.
• Adaptability to various applications resulting in a wide range of applications beyond healthcare.
The many features and advantages of the invention are apparent from the detailed specification, and thus, it is intended by the appended claims to cover all such features and advantages of the invention which fall within the true spirit and scope of the invention. Further, since numerous modifications and variations will readily occur to those skilled in the art, it is not desired to limit the invention to the exact construction and operation illustrated and described, and accordingly, all suitable modifications and equivalents may be resorted to, falling within the scope of the invention.
, Claims:WE CLAIM:
1. An X-Ray detector (100) for CT scan comprising:
a scintillator for converting X-ray to visible light (101);
a lead glass beneath the scintillator for blocking X-Ray (102);
a composite sheet for blocking EMI (103); and
an array of CMOS camera arranged beneath the scintillator (104),
such that each image overlaps the subsequent/adjacent image.

2. The X-Ray detector (100) for CT scan as claimed in claim 1, wherein the scintillator (102) and CMO cameras04)are is same plane to form the image.

3. The X-ray detector (100) for CT scan as claimed in claim 1, wherein the composite sheet is placed between lens and camera and is connected to the ground point of the electronics.

4. The X-ray detector (100) for CT scan as claimed in claim 3, wherein the composite sheet comprises of an aluminum sheet, a lead sheet and a black out fabric.

5. The X-ray detector 100) for CT scan as claimed in claim 4, wherein the aluminum sheet is connected to the electronics ground point, the lead sheet block X-Ray and the black out fabric reduce light coming from back side of the detector.

6. The X-ray detector for (100) CT scan as claimed in claim 1, wherein the plurality of CMOS cameras are arranged equidistance from each other and fastened to the rail through plurality of screws.

7. The X-ray detector (100) for CT scan as claimed in claim 1, wherein the CMO camera is mounted in a rail with polished surface and a groove inside such that there is minimum play between the rail and rectangular block for mounting the camera.

8. A method (200) of creating back projection image slices for CT-scan comprising
an arrangement of CMO cameras, lead glass and scintillator (201) ;
mechanical pre-sets of the CMO camera (202);
software pre-sets of the CMO camera (203);
synchronization among sub-systems (204);
communication of CMO cameras with the computer (105); and
processing of the images (106)
such that all images form a single image in a plane.

9. The method of creating back projection image slices for CT-scan as claimed in claim 8, wherein, the arrangement of CMO camera (201) comprising the steps of
mounting of said CMO camera on a polished surface with plurality of mounting holes (201A);
placing a block on the rail with groove for sliding, fixing and reduced offset, rotation and tilt in the images (201B); and
mounting the rails perpendicular to the stack and parallel to adjacent rails (201C),
such that all the images are aligned without rotation, offset or tilt.

10. The method (200) of creating back projection image slices for CT-scan as claimed in claim 8, wherein the image stitching comprising the steps of set tile configuration, image coordinate selection, image stitching parameter setting and projection image file setting.

11. The method (200) of creating back projection image slices for CT-scan as claimed in claim 8, wherein the mechanical pre-sets (202) are carried out by cross-wire phantom to the center of X-ray image.

12. The method (200) of creating back projection image slices for CT-scan as claimed in claim 8, wherein the software level pre-sets (203) for stitched image correction comprises offset, rotation, tilt and lens distortion correction.

13. The method (200) of creating back projection image slices for CT-scan as claimed in claim 8, wherein the synchronization among sub-systems (204) and communication of camera with the computer system (205) is carried out by first sending it to volatile memory and then to permanent memory, such that images are not lost during communication.

14. The method (200) of creating back projection image slices for CT-scan as claimed in claim 8, wherein the processing of image (206) comprises of performing flat field calibration for each image generated from camera and gray scale equalization for the entire stack of projection images