US20040120464A1 - Cast collimators for CT detectors and methods of making same - Google Patents

Cast collimators for CT detectors and methods of making same Download PDF

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Publication number
US20040120464A1
US20040120464A1 US10/326,020 US32602002A US2004120464A1 US 20040120464 A1 US20040120464 A1 US 20040120464A1 US 32602002 A US32602002 A US 32602002A US 2004120464 A1 US2004120464 A1 US 2004120464A1
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Prior art keywords
collimator
patient
tungsten
filter
collimators
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Abandoned
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US10/326,020
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English (en)
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David Hoffman
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GE Medical Systems Global Technology Co LLC
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Individual
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Priority to US10/326,020 priority Critical patent/US20040120464A1/en
Assigned to GE MEDICAL SYSTEMS GLOBAL TECHNOLOGY COMPANY, LLC reassignment GE MEDICAL SYSTEMS GLOBAL TECHNOLOGY COMPANY, LLC ASSIGNMENT OF ASSIGNORS INTEREST (SEE DOCUMENT FOR DETAILS). Assignors: HOFFMAN, DAVID MICHAEL
Priority to IL159314A priority patent/IL159314A/en
Priority to DE10358866A priority patent/DE10358866A1/de
Priority to JP2003420294A priority patent/JP4630541B2/ja
Priority to NL1025090A priority patent/NL1025090C2/nl
Publication of US20040120464A1 publication Critical patent/US20040120464A1/en
Priority to US11/533,611 priority patent/US7769127B2/en
Priority to US11/552,477 priority patent/US7609804B2/en
Abandoned legal-status Critical Current

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    • G—PHYSICS
    • G21—NUCLEAR PHYSICS; NUCLEAR ENGINEERING
    • G21K—HANDLING OF PARTICLES OR IONISING RADIATION NOT OTHERWISE PROVIDED FOR; IRRADIATION DEVICES; GAMMA RAY OR X-RAY MICROSCOPES
    • G21K1/00—Arrangements for handling particles or ionising radiation, e.g. focusing or moderating
    • G21K1/02—Arrangements for handling particles or ionising radiation, e.g. focusing or moderating using diaphragms, collimators
    • G21K1/025—Arrangements for handling particles or ionising radiation, e.g. focusing or moderating using diaphragms, collimators using multiple collimators, e.g. Bucky screens; other devices for eliminating undesired or dispersed radiation

Definitions

  • the present invention relates generally to collimators for use in computed tomography (CT) imaging systems. More specifically, the present invention relates to cast collimators for use in CT imaging systems, and methods of making same. This invention also relates to filters for use with such collimators, and the choice of material(s) for making such filters and/or collimators.
  • CT computed tomography
  • pre-patient filters and collimators are used to shape an x-ray beam so that a fan-shaped x-ray beam lies within the X-Y plane, or the imaging plane, before its transmission through a patient.
  • These pre-patient filters are generally used to shape the intensity of the x-ray beam in the X-direction, and are commonly enclosed in a housing (i.e., collimator) that determines the width of the x-ray beam in the Z-direction.
  • the filtered and collimated x-ray beam is attenuated by the object being imaged (i.e., the patient having the CT scan performed on them), and the x-rays are then detected by an array of radiation detectors. Often times, the x-rays pass through a post-patient collimator prior to being detected by the array of radiation detectors.
  • These post-patient collimators generally comprise a number of various parts that can be very difficult to accurately align and assemble.
  • the pre-patient collimators often generate significant scattered radiation that subjects the patient to x-ray dose that is not useful in the CT imaging process.
  • Such scatter is becoming an increasing problem as CT manufacturers open up the fan-shaped x-ray beam more and more in the Z-direction to accommodate detectors with more slices and coverage in the Z-direction, thereby increasing the need for better pre-patient and post-patient collimator designs.
  • CT systems are becoming increasingly dose sensitive, it would be desirable to have systems and methods for making pre-patient filter/collimator assemblies that minimize the scattered radiation created therein and exiting therefrom so as to lower the x-ray dose the patient is exposed to.
  • the post-patient collimators are generally complicated structures comprising combs, rails, plates and wires.
  • each comb must be attached to a rail, each plate must be individually inserted into appropriate slots in the combs and be attached thereto, and then wires must be individually strung and attached to the appropriate slots on each plate. This is a very time consuming, labor-intensive process, often requiring reworking if the components are not properly aligned. Therefore, it would be desirable to have systems and methods for making post-patient collimators in an easier, more efficient, and more economical manner than currently possible.
  • Filters used with such collimators could also be better designed to minimize the scattered radiation created therein and exiting therefrom so as to help further lower the x-ray dose the patient is exposed to.
  • collimators both pre-patient and post-patient, that lower the x-ray dose the patient is exposed to by minimizing the scattered radiation created therein or exiting therefrom. It would be further desirable to have such collimators that can be more easily, more accurately, and more efficiently made than currently possible. It would also be desirable to have filters that minimize the scattered radiation created therein and exiting therefrom, for use in combination with such collimators, so as to help further reduce the x-ray dose the patient is exposed to. It would be still further desirable to have such filters and/or collimators be made of one or more cast pieces of a suitable high density, high atomic number material. Finally, it would be desirable to have such collimators to allow improved x-ray dose efficiency. Many other needs will also be met by this invention, as will become more apparent throughout the remainder of the disclosure that follows.
  • embodiments of the present invention which relates to collimators, both pre-patient and post-patient, that lower the x-ray dose the patient is exposed to by minimizing the scattered radiation created therein or exiting therefrom.
  • collimators can be made more easily, more accurately, and more efficiently than currently possible.
  • Embodiments of this invention also comprise filters that minimize the scattered radiation created therein and exiting therefrom, for use in combination with such collimators, so as to help further reduce the x-ray dose the patient is exposed to.
  • filters and/or collimators are preferably made of one or more cast pieces of a suitable high density, high atomic number material. These collimators may allow improved x-ray dose efficiency to be achieved.
  • Embodiments of this invention comprise collimators for use in CT imaging systems.
  • These collimators may comprise a two-dimensional honeycomb structure that comprises channels of a predetermined shape running between channel walls of a predetermined thickness.
  • This two-dimensional honeycomb structure is preferably made via a casting process, and is capable of meeting predetermined precision requirements.
  • a filter operatively coupled thereto, wherein the filter is preferably made of any high-density, high atomic number material such as lead, a lead alloy, tantalum, tungsten, tungsten suspended in an epoxy matrix, tungsten suspended in a slurry, or the like.
  • the filter may be positioned in front of the collimator, or it may comprise a three-dimensional insert that is operatively positioned within the channels of the two-dimensional honeycomb structure.
  • the collimator itself may also be made of any high-density, high atomic number material such as lead, a lead alloy, tantalum, tungsten, tungsten suspended in an epoxy matrix, tungsten suspended in a slurry, or the like.
  • filters for use in pre-patient filter/collimator assemblies in CT imaging systems, or for use in conjunction with post-patient collimators, if so desired.
  • filters preferably comprise any suitable high-density, high atomic number material that is capable of absorbing x-ray radiation, such as lead, a lead alloy, tantalum, tungsten, tungsten suspended in an epoxy matrix, tungsten suspended in a slurry, or the like.
  • Yet other embodiments of this invention comprise pre-patient filter and collimator assemblies for use in CT imaging systems.
  • These assemblies may comprise: a filter component; and a collimator component, wherein the filter component is operatively coupled to the collimator component and the collimator component comprises a two-dimensional honeycomb structure comprising channels of a predetermined shape running between channel walls of a predetermined thickness.
  • the filter and/or the collimator may be made of any suitable high-density, high atomic number material, such as lead, a lead alloy, tantalum, tungsten, tungsten suspended in an epoxy matrix, tungsten suspended in a slurry, or the like.
  • the filter may be positioned in front of the collimator or anywhere else in suitable proximity to the collimator, or it may comprise a three-dimensional insert that is operatively positioned within the channels of the two-dimensional honeycomb structure.
  • Still other embodiments of this invention comprise post-patient collimators for use in CT imaging systems.
  • These collimators preferably comprise: a two-dimensional honeycomb structure comprising channels of a predetermined shape running between channel walls of a predetermined thickness, wherein the two-dimensional honeycomb structure is capable of meeting predetermined precision requirements.
  • these collimators are made via a casting process.
  • the channels in these collimators may comprise any suitable shape, such as rectangular, circular, ovular, trapezoidal, hexagonal, and/or square.
  • these channels are tapered to create a first aperture proximate an x-ray entry surface of the collimator that is larger than a second aperture proximate an x-ray exit surface of the collimator.
  • the two-dimensional honeycomb structure may comprise any suitable high-density, high atomic number material, such as for example lead, a lead alloy, tantalum, tungsten, tungsten suspended in an epoxy matrix, tungsten suspended in a slurry, or the like.
  • FIG. 1 is perspective view of an exemplary CT imaging system
  • FIG. 2 is a perspective view of a high aspect ratio pre-patient collimator as utilized in embodiments of this invention
  • FIG. 3 is a portion of a cross-sectional side view showing some non-tapered, rectangular-shaped vanes and channels as cast in embodiments of this invention.
  • FIG. 4 is a portion of a cross-sectional side view showing some 2-dimensionally tapered, trapezoidal-shaped vanes and channels as cast in other embodiments of this invention.
  • FIGS. 1 - 4 For the purposes of promoting an understanding of the invention, reference will now be made to some preferred embodiments of the present invention as illustrated in FIGS. 1 - 4 , and specific language used to describe the same.
  • the terminology used herein is for the purpose of description, not limitation. Specific structural and functional details disclosed herein are not to be interpreted as limiting, but merely as a basis for the claims as a representative basis for teaching one skilled in the art to variously employ the present invention. Any modifications or variations in the depicted support structures and methods of making same, and such further applications of the principles of the invention as illustrated herein, as would normally occur to one skilled in the art, are considered to be within the spirit of this invention.
  • FIG. 1 shows an exemplary CT imaging system 10 .
  • Such systems generally comprise a gantry 12 , a gantry opening 48 , and a table 46 upon which a patient 22 may lie.
  • Gantry 12 comprises an x-ray source 14 that projects a beam of x-rays 16 toward an array of detector elements 18 .
  • the array of detector elements 18 comprises a plurality of individual detector elements that are arranged in a side-by-side manner in the form of an arc that is essentially centered on x-ray source 14 .
  • parallel rows of arrays of detector elements 18 can be arranged so that each row of detectors can be used to generate a single thin slice image through patient 22 in the X-Y plane.
  • Each detector element in the array of detector elements 18 senses and detects the x-rays 16 that pass through an object, such as patient 22 . While this figure shows the x-ray source 14 and the array of detector elements 18 aligned along the X-axis, some CT imaging systems may align the x-ray source 14 and the array of detector elements 22 differently, such as along the Y-axis or anywhere else in the X-Y plane.
  • pre-patient filters and collimators are utilized between x-ray source 14 and patient 22 to shape the x-ray beam 16 coming from x-ray source 14 before its transmission through patient 22 .
  • the filters in these assemblies tend to shape the intensity of the x-ray beam in the X-direction across the patient 22 , and are commonly enclosed in a housing that determines the width of the x-ray beam in the Z-direction.
  • the housing collimation in Z is achieved by using adjustable collimator blades or jaws to adjust the total area exposed in Z.
  • one major drawback to current pre-patient filter/collimator assemblies is that they often generate significant scattered radiation that subjects the patient to x-ray dose that is not useful in the CT imaging process.
  • Utilizing specific materials for the filters in these pre-patient filter/collimator assemblies may help minimize the scattered radiation generated within the pre-patient filter/collimator assemblies.
  • these filters are made of plastics, Teflon®, Flexan® and/or other low density, low atomic number materials that have a high Compton to total cross section ratio (i.e., their primary attenuation mechanism is via scattering, not via photo-electric absorption).
  • Choosing materials for the filters that have a high photo-electric to total cross section ratio may help minimize the radiation scattered within the filter by reducing or eliminating the scattered radiation creation mechanism.
  • Such materials may include any high atomic number, high density material that is good for absorbing x-rays to minimize x-ray scatter, such as for example, lead, a lead alloy, tantalum, tungsten, tungsten suspended in an epoxy matrix, tungsten suspended in a slurry, or any other high density, high atomic number material that is capable of optimizing X-ray absorption.
  • the collimators may also benefit from being made from the same high density, high atomic number materials as the filters.
  • the filters and collimators may comprise a single material, a stack of materials, or a composite material.
  • the pre-patient scattered radiation could be further reduced by positioning a honeycomb-shaped collimator 200 proximate a filter, to filter out even more of the scattered radiation, especially the forward scattered radiation that is directed at the patient.
  • a honeycomb-shaped collimator 200 proximate a filter, to filter out even more of the scattered radiation, especially the forward scattered radiation that is directed at the patient.
  • This pre-patient filter/collimator assembly may comprise utilizing a three-dimensional insert in the Z-slice width collimator that has small holes in it, which effectively acts as a high aspect ratio collimator to absorb the scattered radiation that may be generated in the filter positioned in front of the pre-patient collimator.
  • Such an assembly would preferably be made by a casting process, which would allow honeycomb structures having very thin walls or vanes to be made. High density, high atomic number materials could be used to make such honeycomb structures to further help minimize the scattered radiation, and thereby reduce the x-ray dose to the patient.
  • the filter material could be positioned within the honeycomb structure itself, similar to honey in a honeycomb.
  • stacked etched foils could be used, or plate-plate egg crate assemblies could be used.
  • the pre-patient filter/collimator assemblies comprise a specially-selected, high atomic number, high density material for the filter, and a high aspect ratio collimator having small channels therein operatively coupled to the filter.
  • This collimator 200 may comprise a cast 2-dimensional honeycomb structure, such as that shown in FIG. 2, where the honeycomb structure comprises small rectangular-shaped channels 211 running throughout the depth 220 of the collimator 200 . Casting such a structure is preferable because it allows small apertures in between very thin walls to be created.
  • cast structures may comprise a single cast piece, or multiple cast pieces that may be joined together.
  • pre-patient and post-patient collimators comprise radial assemblies that are focused at the x-ray tube focal spot.
  • Many CT imaging systems also utilize post-patient collimators between the patient 22 and the array of detector elements 18 to focus the attenuated x-rays 16 that pass through patient 22 onto the various detector elements in the array of detector elements 18 .
  • Current post-patient collimators comprise numerous precision or semi-precision machined or fabricated parts that must be precisely positioned and assembled, one at a time, by hand.
  • the post-patient collimators of this invention are preferably made via casting, which allows thin, tapered vanes to be created, thereby reducing non-linearities and image artifacts commonly caused by misaligned collimator vanes in existing post-patient collimators.
  • Non-linearities in existing post-patient collimators may be caused when the x-ray source moves slightly during operation, as is common due to the heat generated by the rotating anode within the x-ray generation source, thereby causing the x-ray beams to be aligned in a non-parallel manner with respect to the channels in the collimator, resulting in shadowing at the x-ray exit surface 215 of the collimator.
  • Such non-linearities are often corrected in existing post-patient collimators by skewing the vanes to slightly misalign the plates in the collimator; this greatly reduces the channel-to-channel nonlinearities induced by focal spot motion of the x-ray beam during operation.
  • Casting these post-patient collimators may help improve x-ray dose utilization and efficiency by allowing thinner, tapered vanes to be used therein, thereby eliminating the need to skew the vanes. It would be almost inconceivable to create tapered vanes in any manner other than casting.
  • These cast channels could be tapered in one dimension or two, whichever is desired.
  • these channels may be tapered in only the X-direction or the Y-direction (i.e., 1-D taper), or they could be tapered in both the X-direction and the Y-direction (i.e., 2-D taper).
  • X-direction or the Y-direction i.e., 1-D taper
  • 2-D taper i.e., 2-D taper
  • casting allows various other shaped vanes and channels to be formed therein, such as for example round channels or hexagonal channels, both of which could also be tapered in one dimension or two, whichever may be desired.
  • FIG. 3 A portion of a cross-sectional side view showing some non-tapered, rectangular-shaped vanes 210 and rectangular-shaped channels 211 , as cast in embodiments of this invention, can be seen in FIG. 3.
  • FIG. 4 A portion of a cross-sectional side view showing some tapered, trapezoidal-shaped vanes 212 and trapezoidal-shaped channels 213 , as cast in other embodiments of this invention, is shown in FIG. 4. It will be apparent to those skilled in the art that numerous other shaped channels could be created in these collimators, and all such variations are deemed to be within the scope of this invention.
  • tapeering the vanes may also eliminate the varying shadowing effects that are commonly caused by misaligned collimator vanes in existing post-patient collimators. Furthermore, tapering the vanes eliminates the need to skew the vanes, as is commonly done in existing post-patient collimators to improve x-ray dose efficiency.
  • the vanes and channels in these pre-patient and post-patient collimators do not have to be tapered.
  • the honeycomb structure of these collimators can be made with 2-dimensional septa, 1-dimensional septa, or the equivalent of the current plates and wires used in such collimators.
  • numerous cast designs of these collimators are possible.
  • the collimators may be cast as single piece structures, or they may be cast as multiple pieces that are capable of being operatively coupled together.
  • the systems and methods of the present invention allow both the pre-patient and post-patient collimators to be made via a casting process, allowing very accurate collimators to be made much easier and more economically than currently possible.
  • these collimators also help minimize scattered x-ray radiation, thereby reducing the x-ray dose that patients are exposed to.
  • the materials selected for making such collimators may help minimize the scattered radiation that is being created within such collimator assemblies or scattered therefrom, and the honeycomb structures may help further reduce the scattered radiation that patients are subjected to. This is particularly advantageous since CT imaging systems are becoming more dose sensitive, and it is desirable to expose the patient to no more radiation than necessary.

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  • Physics & Mathematics (AREA)
  • Spectroscopy & Molecular Physics (AREA)
  • Engineering & Computer Science (AREA)
  • General Engineering & Computer Science (AREA)
  • High Energy & Nuclear Physics (AREA)
  • Apparatus For Radiation Diagnosis (AREA)
  • Nuclear Medicine (AREA)
  • Measurement Of Radiation (AREA)
US10/326,020 2002-12-19 2002-12-19 Cast collimators for CT detectors and methods of making same Abandoned US20040120464A1 (en)

Priority Applications (7)

Application Number Priority Date Filing Date Title
US10/326,020 US20040120464A1 (en) 2002-12-19 2002-12-19 Cast collimators for CT detectors and methods of making same
IL159314A IL159314A (en) 2002-12-19 2003-12-11 Cast collimators for ct detectors and methods of making same
DE10358866A DE10358866A1 (de) 2002-12-19 2003-12-16 Gegossene Kollimatoren für CT Detektoren und Verfahren zu ihre Herstellung
JP2003420294A JP4630541B2 (ja) 2002-12-19 2003-12-18 Ｃｔ検出器用の鋳造コリメータ及びその製作方法
NL1025090A NL1025090C2 (nl) 2002-12-19 2003-12-19 Gegoten collimatoren voor CT-detectoren en werkwijzen voor het maken hiervan.
US11/533,611 US7769127B2 (en) 2002-12-19 2006-09-20 Pre-subject filters for CT detectors and methods of making same
US11/552,477 US7609804B2 (en) 2002-12-19 2006-10-24 Cast collimators for CT detectors and methods of making same

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US10/326,020 US20040120464A1 (en) 2002-12-19 2002-12-19 Cast collimators for CT detectors and methods of making same

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US11/533,611 Continuation US7769127B2 (en) 2002-12-19 2006-09-20 Pre-subject filters for CT detectors and methods of making same

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US11/533,611 Expired - Lifetime US7769127B2 (en) 2002-12-19 2006-09-20 Pre-subject filters for CT detectors and methods of making same
US11/552,477 Expired - Fee Related US7609804B2 (en) 2002-12-19 2006-10-24 Cast collimators for CT detectors and methods of making same

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US7609804B2 (en) 2009-10-27
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DE10358866A1 (de) 2004-09-30
US20070025501A1 (en) 2007-02-01
IL159314A (en) 2010-11-30
JP2004195235A (ja) 2004-07-15
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JP4630541B2 (ja) 2011-02-09
US20070064876A1 (en) 2007-03-22

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