US20020087073A1 - CT detector reflector useful in detector scintillator array - Google Patents
CT detector reflector useful in detector scintillator array Download PDFInfo
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- US20020087073A1 US20020087073A1 US09/751,872 US75187200A US2002087073A1 US 20020087073 A1 US20020087073 A1 US 20020087073A1 US 75187200 A US75187200 A US 75187200A US 2002087073 A1 US2002087073 A1 US 2002087073A1
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- reflective film
- scintillators
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01T—MEASUREMENT OF NUCLEAR OR X-RADIATION
- G01T1/00—Measuring X-radiation, gamma radiation, corpuscular radiation, or cosmic radiation
- G01T1/16—Measuring radiation intensity
- G01T1/20—Measuring radiation intensity with scintillation detectors
- G01T1/2002—Optical details, e.g. reflecting or diffusing layers
Definitions
- This invention relates generally to a computer tomograph (CT) imaging system and more particularly to a CT detector module and reflector useful therewith and to methods for preparing and using the detector module and reflector.
- CT computer tomograph
- an x-ray source projects a fan-shaped beam which is collimated to lie within an X-Y plane of a Cartesian coordinate system and generally referred to as the “imaging plane”.
- the x-ray beam passes through the object being imaged, such as a patient.
- the beam after being attenuated by the object, impinges upon an array of radiation detectors.
- the intensity of the attenuated beam radiation received at the detector array is dependent upon the attenuation of the x-ray beam by the object.
- Each detector element of the array produces a separate electrical signal that is a measurement of the beam attenuation at the detector location.
- the attenuation measurements from all the detectors are acquired separately to produce a transmission profile.
- the x-ray source and the detector array are rotated with a gantry within the imaging plane and around the object to be imaged so that the angle at which the x-ray beam intersects the object constantly changes.
- a group of x-ray attenuation measurements, i.e., projection data, from the detector array at one gantry angle is referred to as a “view”.
- a “scan” of the object comprises a set of views made at different gantry angles, or view angles, during one revolution of the x-ray source and detector.
- the projection data is processed to construct an image that corresponds to a two-dimensional slice taken through the object.
- CT numbers integers called “CT numbers” or “Hounsfield units”, which are used to control the brightness of a corresponding pixel on a cathode ray tube display.
- At least one known detector in CT imaging systems comprises a plurality of detector modules, each having a scintillator array optically coupled to a semiconductor photodiode array that detects light output by the scintillator array.
- These known detector module assemblies require an adhesive bonding operation to assemble.
- the photodiode array and scintillator must be accurately aligned with an alignment system, using a plastic shim to set a gap between the photodiode and scintillator arrays. After alignment, the four comers of the assembly are “tacked” together with an adhesive to hold the alignment.
- the tack is cured, and the thin gap between the photodiode and scintillator arrays is filled by dipping the assembly into an optical epoxy adhesive, which wicks into the entire gap.
- the epoxy is cured, and the scintillator is thus “epoxied” to the diode array.
- a cast reflector is made of a two part epoxy and a chrome pigment used in one known typical CT semiconductor photodiode detector array. Such cast reflectors are sometimes damaged by X-ray exposure which causes color center formation, reduces reflectivity and causes lower light output from each photodiode detector cell, i.e., quantum detector efficiency (QDE). Cast reflectors are protected by tungsten wires and plates in known CT systems and have a certain thickness to sufficiently reduce cross talk. Cast reflectors are typically produced in a casting process whereby the epoxy is cast in molds.
- QDE quantum detector efficiency
- a computed tomograph (CT) imaging system having a rotating gantry, a radiation source, a detector array on the rotating gantry and configured to detect radiation from the radiation source and the detector array.
- the detector array includes a photosensor array and an array of scintillators optically coupled to the photosensor array and a thermoplastic encased reflective film between the scintillators of the scintillator array.
- the reflector is thin and is less susceptible to x-ray damage.
- FIG. 1 is a pictorial view of a CT imaging system.
- FIG. 2 is a block schematic diagram of the system illustrated in FIG. 1.
- FIG. 3 is a perspective view of a CT system detector array.
- FIG. 4 is a perspective view of a detector module shown in FIG. 3.
- FIG. 5 presents an overview of several embodiments of a process for preparing an improved reflector and further illustrates placement of a reflector within a photodiode array.
- a computed tomography (CT) imaging system 10 is shown as including a gantry 12 representative of a “third generation” CT scanner.
- Gantry 12 has an x-ray source 14 that projects a beam of x-rays 16 toward a detector array 18 on the opposite side of gantry 12 .
- Detector array 18 is formed by detector elements 20 which together sense the projected x-rays that pass through an object 22 , for example a medical patient.
- Each detector element 20 produces an electrical signal that represents the intensity of an impinging x-ray beam and hence the attenuation of the beam as it passes through patient 22 .
- Detector array 18 may be fabricated in a single slice or multi-slice configuration. In a multi-slice configuration, detector array 18 has a plurality of rows of detector elements 20 , only one of which is shown in FIG. 2.
- Control mechanism 26 includes an x-ray controller 28 that provides power and timing signals to x-ray source 14 and a gantry motor controller 30 that controls the rotational speed and position of gantry 12 .
- a data acquisition system (DAS) 32 in control mechanism 26 samples analog data from detector elements 20 and converts the data to digital signals for subsequent processing.
- An image reconstructor 34 receives sampled and digitized x-ray data from DAS 32 and performs high speed image reconstruction. The reconstructed image is applied as an input to a computer 36 which stores the image in a mass storage device 38 .
- DAS data acquisition system
- Computer 36 also receives commands and scanning parameters from an operator via console 40 that has a keyboard.
- An associated cathode ray tube display 42 allows the operator to observe the reconstructed image and other data from computer 36 .
- the operator supplied commands and parameters are used by computer 36 to provide control signals and information to DAS 32 , x-ray controller 28 and gantry motor controller 30 .
- computer 36 operates a table motor controller 44 which controls a motorized table 46 to position patient 22 in gantry 12 . Particularly, table 46 moves portions of patient 22 through gantry opening 48 .
- detector array 18 includes a plurality of detector modules 50 , each module comprising an array of detector elements 20 .
- Each detector module 50 includes a high-density photosensor array 52 and a multidimensional scintillator array 54 positioned above and adjacent to photosensor array 52 .
- scintillator array 54 includes a plurality of scintillators 56
- photosensor array 52 includes photodiodes 58 , a switch apparatus 60 , and a decoder 62 .
- a material such as a titanium dioxide-filled epoxy fills the small spaces between scintillator elements.
- Photodiodes 58 are individual photodiodes.
- photodiodes 58 are a multidimensional diode array. In either embodiment, photodiodes 58 are deposited or formed on a substrate. Scintillator array 54 , as known in the art, is positioned over or adjacent photodiodes 58 . Photodiodes 58 are optically coupled to scintillator array 54 and have electrical output lines for transmitting signals representative of the light output by scintillator array 54 . Each photodiode 58 produces a separate low level analog output signal that is a measurement of beam attenuation for a specific scintillator of scintillator array 54 . Photodiode output lines (not shown in FIGS. 3 or 4 ) may, for example, be physically located on one side of module 20 or on a plurality of sides of module 20 . In the embodiment illustrated in FIG. 4, photodiode outputs are located at opposing sides of the photodiode array.
- detector array 18 includes fifty-seven detector modules 50 .
- Each detector module 50 includes a photosensor array 52 and scintillator array 54 , each having a detector element 20 array size of 16 ⁇ 16.
- Switch apparatus 60 is a multidimensional semiconductor switch array. Switch apparatus 60 is coupled between photosensor array 52 and DAS 32 .
- Switch apparatus 60 in one embodiment, includes two semiconductor switch arrays 64 and 66 .
- Switch arrays 64 and 66 each include a plurality of field effect transistors (FETS) (not shown) arranged as a multidimensional array.
- FETS field effect transistors
- Each FET includes an input electrically connected to one of the respective photodiode output lines, an output, and a control (not shown) arranged as a multidimensional array.
- Each FET includes an input electrically connected to one of the respective photodiode output lines, an output, and a control (not shown). FET outputs and controls are connected to lines that are electrically connected to DAS 32 via a flexible electrical cable 68 .
- each FET input line of switch 64 with the other one-half of photodiode output lines electrically connected to DAS 32 via a flexible electrical cable 68 .
- Particularly about one-half of the photodiode output lines are electrically connected to each FET input line of switch 64 with the other one-half of photodiode output lines electrically connected to FET input lines of switch 66 .
- Flexible electrical cable 68 is thus electrically coupled to photosensor array 52 and is attached, for example, by wire bonding.
- Decoder 63 controls the operation of switch apparatus 60 to enable, disable, or combine photodiode 58 outputs depending upon a desired number of slices and slice resolution for each slide.
- Decoder 62 in one embodiment, is an FET controller as known in the art. Decoder 62 includes a plurality of output and control lines coupled to switch apparatus 60 and DAS 32 . Particularly, the decoder outputs are electrically coupled to the switch apparatus control lines to enable switch apparatus 60 to transmit the proper data from the switch apparatus inputs to the switch apparatus outputs.
- decoder 62 Utilizing decoder 62 , specific FES within switch apparatus 60 are selectively enabled, disabled, or combined so that specific photodiode 58 outputs are electrically connected to CT system DAS 32 . Decoder 62 enables switch apparatus 60 so that a selected number of rows of photosensor array 52 are connected to DAS 32 , resulting in a selected number of slices of data being electrically connected to DAS 32 for processing.
- FIG. 3 shows rail 72 secured in place, while rail 70 is positioned to be secured over electrical cable 68 , over module substrate 74 , flexible cable 68 , and mounting bracket 76 . Screws (not shown in FIGS. 3 or 4 ) are then threaded through holes 78 and 80 and into threaded holes 82 of rail 70 to secure modules 50 in place. Flanges 84 of mounting brackets 76 are held in place by compression against rails 70 and 72 (or by bonding, in one embodiment) and prevent detector modules 50 from “rocking”. Mounting brackets 76 also clamp flexible cable 68 against substrate 74 , in one embodiment, flexible cable 68 is also adhesively bonded to substrate 74 .
- photosensor array can be adhesively bonded to the substrate.
- Flexible cable 68 is also electrically and mechanically bonded to photosensor array 52 , for example, by wire bonding.
- a region (not shown) is provided on each side of photosensor array 52 to provide room to wire bond cable (not shown).
- conductors of flex cable (not shown) are directly wire bonded to circuits on photosensor array 52 , including switch apparatus 60 and decoder 62 .
- Brackets (not shown) are adhesively affixed to scintillator array 54 at an interface (not shown) and to substrate 74 at an interface (not shown). Screws (not shown) are fitted into holes 78 and 80 , but are not relied upon to clamp scintillator array 54 in place. The clamping mechanism provided by brackets (not shown) holds scintillator array 54 in place and separates scintillator array 54 from photosensor array 52 .
- a cast reflector is used between elements (not shown), the cast reflector including at least one thermoplastic film (not shown).
- Suitable encasement material for the reflective film used herein includes but is not limited to a thermoplastic.
- thermoplastic includes any material which has in whole or part, a linear macromolecular structure that will repeatedly soften when heated and harden when cooled.
- a thermoplastic is used that is readily malleable and flexible at room temperature for fabrication purposes, offers higher resistance to color center formation and provides resistance to X-ray radiation damage.
- the thermoplastic either has an adhesive surface or is capable of adhering to a surface upon which an adhesive has been applied.
- thermoplastic material is capable of being bonded to as by being laminated with or stuck to the reflective film.
- reflective films useful herein include 3M visible mirror film, Hitachi and NKK TiO2 doped plastic films.
- the thickness of the “encased” reflector is such that an outside dimension is accommodated by an interior fit or placement within the semiconductor photodiode detector.
- the stack is thereafter heated, pressure is applied if necessary to effectively bonded the wafer stack together sufficiently adherent to accommodate a subsequent slicing.
- the other dimensions of the encased reflective film will be in general accordance with the dimensions of the wafers with which the film is to be utilized.
- a 22 mm scintillator wafer is stacked vertically upon one another of several others of similar kind and similar size, creating a 0.002 vertical gap 106 between adjacent stacked wafers 108 .
- Gaps 106 are then filled with a reflector of this invention which in turn comprises a thermoplastic film (not shown), a reflector film (not shown) and another thermoplastic film (not shown) with reflector film (not shown) sandwiched therebetween by laminating reflector film (not shown) between thermoplastic films (not shown).
- thermoplastic film is inserted in gap 106
- a reflective film is then inserted between the inserted thermoplastic film and an adjacent wafer face in gap 106 remaining open
- a second thermoplastic film is inserted in gap 106 remaining open, between the inserted reflective film face and an adjacent wafer face thus closing gap 106 .
- Suitable heat and pressure are applied to the wafer stack to carry out effective lamination of the thermoplastic and reflective film and achieving adherence to the wafers in stack 108 .
- Lamination of a thermoplastic to a reflective film in embodiments of the present invention are readily carried out according to lamination processes known in the art.
- a series of parallel vertical cuts 110 is made on stack 108 using a suitable cutting or dicing tool creating a section 112 .
- cuts are made to provide a stack 112 having a thickness of about 1.5 mm.
- Section 112 is laid down flat. Additional such sections 114 similar to section 112 are created. These sections can then be cast together into a final packet.
- thermoplastic material can be any suitable thermoplastic adhesive material.
- additional heat and pressure are not necessary to carry out effective bonding between the reflective film and thermoplastic films creating an encased reflective film. Because the thermoplastic and reflective film are held together by adhesive which is applied to either the thermoplastic or reflective film.
- a reflective film is deposited directly onto a thermoplastic sheet and is then laminated with another layer of thermoplastic material. The laminated reflective material is then inserted into the gap between the wafers.
- a bar is created by a second cut in a stack of wafers. Bars are laid down in an array creating gaps. These gaps are then filled with the reflector material including a reflective film.
- Embodiments of the present invention use thin reflective film in one or two dimensions of the scintillator array, that are less susceptible to radiation damage and more resistant to color center formation than known cast reflectors.
- Use of improved reflector embodiments of the present invention in one or more dimensions makes it possible to avoid the use of collimator wires, thereby providing a beneficial cost savings.
- the elimination of collimator wires and use of potentially thinner reflectors allows use of detectors to acquire data representation of thinner slices in the z-direction.
- Laminates can be thinner than current cast materials and advantageously provide for more exposed scintillator.
Abstract
A method for making a detector array comprising a photosensor and scintillators, including placing a thermoplastically encased reflective film between scintillators of a scintillator array and optically coupling the scintillators with the photo sensor.
Description
- This invention relates generally to a computer tomograph (CT) imaging system and more particularly to a CT detector module and reflector useful therewith and to methods for preparing and using the detector module and reflector.
- In at least one known computed tomography (CT) imaging system configuration, an x-ray source projects a fan-shaped beam which is collimated to lie within an X-Y plane of a Cartesian coordinate system and generally referred to as the “imaging plane”. The x-ray beam passes through the object being imaged, such as a patient. The beam, after being attenuated by the object, impinges upon an array of radiation detectors. The intensity of the attenuated beam radiation received at the detector array is dependent upon the attenuation of the x-ray beam by the object. Each detector element of the array produces a separate electrical signal that is a measurement of the beam attenuation at the detector location. The attenuation measurements from all the detectors are acquired separately to produce a transmission profile.
- In known third generation CT systems, the x-ray source and the detector array are rotated with a gantry within the imaging plane and around the object to be imaged so that the angle at which the x-ray beam intersects the object constantly changes. A group of x-ray attenuation measurements, i.e., projection data, from the detector array at one gantry angle is referred to as a “view”. A “scan” of the object comprises a set of views made at different gantry angles, or view angles, during one revolution of the x-ray source and detector. In an axial scan, the projection data is processed to construct an image that corresponds to a two-dimensional slice taken through the object. One method for reconstructing an image from a set of projection data is referred to in the art as the filtered back projection technique. This process converts the attenuation measurements from a scan into integers called “CT numbers” or “Hounsfield units”, which are used to control the brightness of a corresponding pixel on a cathode ray tube display.
- At least one known detector in CT imaging systems comprises a plurality of detector modules, each having a scintillator array optically coupled to a semiconductor photodiode array that detects light output by the scintillator array. These known detector module assemblies require an adhesive bonding operation to assemble. The photodiode array and scintillator must be accurately aligned with an alignment system, using a plastic shim to set a gap between the photodiode and scintillator arrays. After alignment, the four comers of the assembly are “tacked” together with an adhesive to hold the alignment. The tack is cured, and the thin gap between the photodiode and scintillator arrays is filled by dipping the assembly into an optical epoxy adhesive, which wicks into the entire gap. The epoxy is cured, and the scintillator is thus “epoxied” to the diode array.
- A cast reflector is made of a two part epoxy and a chrome pigment used in one known typical CT semiconductor photodiode detector array. Such cast reflectors are sometimes damaged by X-ray exposure which causes color center formation, reduces reflectivity and causes lower light output from each photodiode detector cell, i.e., quantum detector efficiency (QDE). Cast reflectors are protected by tungsten wires and plates in known CT systems and have a certain thickness to sufficiently reduce cross talk. Cast reflectors are typically produced in a casting process whereby the epoxy is cast in molds.
- Accordingly it would be desirable to provide an improved reflector which is comparatively less susceptible to radiation damage, offers enhanced resistance to color center formation and provides improved detector QDE.
- There is therefore provided in one embodiment of this invention, a computed tomograph (CT) imaging system having a rotating gantry, a radiation source, a detector array on the rotating gantry and configured to detect radiation from the radiation source and the detector array. The detector array includes a photosensor array and an array of scintillators optically coupled to the photosensor array and a thermoplastic encased reflective film between the scintillators of the scintillator array. The reflector is thin and is less susceptible to x-ray damage.
- These and other embodiments of the invention provide various combinations of additional advantages, including lower manufacturing cost due to use of a lamination reflector fabrication process, and lower cross talk.
- FIG. 1 is a pictorial view of a CT imaging system.
- FIG. 2 is a block schematic diagram of the system illustrated in FIG. 1.
- FIG. 3 is a perspective view of a CT system detector array.
- FIG. 4 is a perspective view of a detector module shown in FIG. 3.
- FIG. 5 presents an overview of several embodiments of a process for preparing an improved reflector and further illustrates placement of a reflector within a photodiode array.
- Referring to FIGS. 1 and 2, a computed tomography (CT)
imaging system 10 is shown as including agantry 12 representative of a “third generation” CT scanner. Gantry 12 has anx-ray source 14 that projects a beam ofx-rays 16 toward adetector array 18 on the opposite side ofgantry 12.Detector array 18 is formed bydetector elements 20 which together sense the projected x-rays that pass through anobject 22, for example a medical patient. Eachdetector element 20 produces an electrical signal that represents the intensity of an impinging x-ray beam and hence the attenuation of the beam as it passes throughpatient 22. During a scan to acquire x-ray projection data,gantry 12 and the components mounted thereon rotate about a center ofrotation 24.Detector array 18 may be fabricated in a single slice or multi-slice configuration. In a multi-slice configuration,detector array 18 has a plurality of rows ofdetector elements 20, only one of which is shown in FIG. 2. - Rotation of
gantry 12 and the operation ofx-ray source 14 are governed by acontrol mechanism 26 ofCT system 10.Control mechanism 26 includes anx-ray controller 28 that provides power and timing signals tox-ray source 14 and agantry motor controller 30 that controls the rotational speed and position ofgantry 12. A data acquisition system (DAS) 32 incontrol mechanism 26 samples analog data fromdetector elements 20 and converts the data to digital signals for subsequent processing. Animage reconstructor 34 receives sampled and digitized x-ray data fromDAS 32 and performs high speed image reconstruction. The reconstructed image is applied as an input to acomputer 36 which stores the image in amass storage device 38. -
Computer 36 also receives commands and scanning parameters from an operator viaconsole 40 that has a keyboard. An associated cathoderay tube display 42 allows the operator to observe the reconstructed image and other data fromcomputer 36. The operator supplied commands and parameters are used bycomputer 36 to provide control signals and information toDAS 32,x-ray controller 28 andgantry motor controller 30. In addition,computer 36 operates atable motor controller 44 which controls a motorized table 46 to positionpatient 22 ingantry 12. Particularly, table 46 moves portions ofpatient 22 throughgantry opening 48. - As shown in FIGS. 3 and 4,
detector array 18 includes a plurality ofdetector modules 50, each module comprising an array ofdetector elements 20. Eachdetector module 50 includes a high-density photosensor array 52 and amultidimensional scintillator array 54 positioned above and adjacent to photosensor array 52. Particularly,scintillator array 54 includes a plurality of scintillators 56, while photosensor array 52 includesphotodiodes 58, a switch apparatus 60, and adecoder 62. A material such as a titanium dioxide-filled epoxy fills the small spaces between scintillator elements.Photodiodes 58 are individual photodiodes. In another embodiment,photodiodes 58 are a multidimensional diode array. In either embodiment,photodiodes 58 are deposited or formed on a substrate.Scintillator array 54, as known in the art, is positioned over oradjacent photodiodes 58.Photodiodes 58 are optically coupled toscintillator array 54 and have electrical output lines for transmitting signals representative of the light output byscintillator array 54. Eachphotodiode 58 produces a separate low level analog output signal that is a measurement of beam attenuation for a specific scintillator ofscintillator array 54. Photodiode output lines (not shown in FIGS. 3 or 4) may, for example, be physically located on one side ofmodule 20 or on a plurality of sides ofmodule 20. In the embodiment illustrated in FIG. 4, photodiode outputs are located at opposing sides of the photodiode array. - In one embodiment, as shown in FIG. 3,
detector array 18 includes fifty-sevendetector modules 50. Eachdetector module 50 includes a photosensor array 52 andscintillator array 54, each having adetector element 20 array size of 16×16. As a result,array 18 is segmented into 16 rows and 912 columns (16×57 modules) allowing up to N=16 simultaneous slices of data to be collected along a z-axis with each rotation ofgantry 12, where the z-axis is an axis of rotation of the gantry. - Switch apparatus60 is a multidimensional semiconductor switch array. Switch apparatus 60 is coupled between photosensor array 52 and
DAS 32. Switch apparatus 60, in one embodiment, includes twosemiconductor switch arrays 64 and 66.Switch arrays 64 and 66 each include a plurality of field effect transistors (FETS) (not shown) arranged as a multidimensional array. Each FET includes an input electrically connected to one of the respective photodiode output lines, an output, and a control (not shown) arranged as a multidimensional array. - Each FET includes an input electrically connected to one of the respective photodiode output lines, an output, and a control (not shown). FET outputs and controls are connected to lines that are electrically connected to
DAS 32 via a flexibleelectrical cable 68. - Particularly, about one-half of the photodiode output lines are electrically connected to each FET input line of
switch 64 with the other one-half of photodiode output lines electrically connected toDAS 32 via a flexibleelectrical cable 68. Particularly about one-half of the photodiode output lines are electrically connected to each FET input line ofswitch 64 with the other one-half of photodiode output lines electrically connected to FET input lines of switch 66. Flexibleelectrical cable 68 is thus electrically coupled to photosensor array 52 and is attached, for example, by wire bonding. - Decoder63 controls the operation of switch apparatus 60 to enable, disable, or combine
photodiode 58 outputs depending upon a desired number of slices and slice resolution for each slide.Decoder 62 in one embodiment, is an FET controller as known in the art.Decoder 62 includes a plurality of output and control lines coupled to switch apparatus 60 andDAS 32. Particularly, the decoder outputs are electrically coupled to the switch apparatus control lines to enable switch apparatus 60 to transmit the proper data from the switch apparatus inputs to the switch apparatus outputs. - Utilizing
decoder 62, specific FES within switch apparatus 60 are selectively enabled, disabled, or combined so thatspecific photodiode 58 outputs are electrically connected toCT system DAS 32.Decoder 62 enables switch apparatus 60 so that a selected number of rows of photosensor array 52 are connected toDAS 32, resulting in a selected number of slices of data being electrically connected toDAS 32 for processing. - As shown in FIG. 3,
detector modules 50 are filled in adetector array 18 and secured in place byrails rail 72 secured in place, whilerail 70 is positioned to be secured overelectrical cable 68, overmodule substrate 74,flexible cable 68, and mountingbracket 76. Screws (not shown in FIGS. 3 or 4) are then threaded throughholes 78 and 80 and into threadedholes 82 ofrail 70 to securemodules 50 in place.Flanges 84 of mountingbrackets 76 are held in place by compression againstrails 70 and 72 (or by bonding, in one embodiment) and preventdetector modules 50 from “rocking”. Mountingbrackets 76 also clampflexible cable 68 againstsubstrate 74, in one embodiment,flexible cable 68 is also adhesively bonded tosubstrate 74. - If desired, photosensor array can be adhesively bonded to the substrate.
Flexible cable 68 is also electrically and mechanically bonded to photosensor array 52, for example, by wire bonding. - A region (not shown) is provided on each side of photosensor array52 to provide room to wire bond cable (not shown). In one embodiment, conductors of flex cable (not shown) are directly wire bonded to circuits on photosensor array 52, including switch apparatus 60 and
decoder 62. Brackets (not shown) are adhesively affixed toscintillator array 54 at an interface (not shown) and tosubstrate 74 at an interface (not shown). Screws (not shown) are fitted intoholes 78 and 80, but are not relied upon to clampscintillator array 54 in place. The clamping mechanism provided by brackets (not shown) holdsscintillator array 54 in place and separatesscintillator array 54 from photosensor array 52. - With reference to FIG. 5, to improve quantum detection efficiency of detector elements (not shown) in detector array (not shown), a cast reflector is used between elements (not shown), the cast reflector including at least one thermoplastic film (not shown). Suitable encasement material for the reflective film used herein includes but is not limited to a thermoplastic. As used herein, the term “thermoplastic” includes any material which has in whole or part, a linear macromolecular structure that will repeatedly soften when heated and harden when cooled. In one embodiment, a thermoplastic is used that is readily malleable and flexible at room temperature for fabrication purposes, offers higher resistance to color center formation and provides resistance to X-ray radiation damage. Also in one embodiment, the thermoplastic either has an adhesive surface or is capable of adhering to a surface upon which an adhesive has been applied.
- In one embodiment, the thermoplastic material is capable of being bonded to as by being laminated with or stuck to the reflective film.
- In one embodiment, reflective films useful herein include 3M visible mirror film, Hitachi and NKK TiO2 doped plastic films.
- The thickness of the “encased” reflector is such that an outside dimension is accommodated by an interior fit or placement within the semiconductor photodiode detector. Upon insertion of the reflector of this invention into a gap of the wafer stack, the stack is thereafter heated, pressure is applied if necessary to effectively bonded the wafer stack together sufficiently adherent to accommodate a subsequent slicing. The other dimensions of the encased reflective film will be in general accordance with the dimensions of the wafers with which the film is to be utilized.
- With reference to FIG. 5, in one embodiment, a 22 mm scintillator wafer is stacked vertically upon one another of several others of similar kind and similar size, creating a 0.002
vertical gap 106 between adjacentstacked wafers 108.Gaps 106 are then filled with a reflector of this invention which in turn comprises a thermoplastic film (not shown), a reflector film (not shown) and another thermoplastic film (not shown) with reflector film (not shown) sandwiched therebetween by laminating reflector film (not shown) between thermoplastic films (not shown). - With further reference to FIG. 5, in this embodiment, in more detail, a first thermoplastic film is inserted in
gap 106, a reflective film is then inserted between the inserted thermoplastic film and an adjacent wafer face ingap 106 remaining open, and thereafter a second thermoplastic film is inserted ingap 106 remaining open, between the inserted reflective film face and an adjacent wafer face thus closinggap 106. Suitable heat and pressure are applied to the wafer stack to carry out effective lamination of the thermoplastic and reflective film and achieving adherence to the wafers instack 108. Lamination of a thermoplastic to a reflective film in embodiments of the present invention are readily carried out according to lamination processes known in the art. - A series of parallel
vertical cuts 110 is made onstack 108 using a suitable cutting or dicing tool creating asection 112. In one embodiment, cuts are made to provide astack 112 having a thickness of about 1.5 mm.Section 112 is laid down flat. Additionalsuch sections 114 similar tosection 112 are created. These sections can then be cast together into a final packet. - In an embodiment and with continued reference to FIG. 5, thermoplastic material can be any suitable thermoplastic adhesive material. In this embodiment additional heat and pressure are not necessary to carry out effective bonding between the reflective film and thermoplastic films creating an encased reflective film. Because the thermoplastic and reflective film are held together by adhesive which is applied to either the thermoplastic or reflective film.
- In an embodiment, a reflective film is deposited directly onto a thermoplastic sheet and is then laminated with another layer of thermoplastic material. The laminated reflective material is then inserted into the gap between the wafers.
- In an embodiment, a bar is created by a second cut in a stack of wafers. Bars are laid down in an array creating gaps. These gaps are then filled with the reflector material including a reflective film.
- Embodiments of the present invention use thin reflective film in one or two dimensions of the scintillator array, that are less susceptible to radiation damage and more resistant to color center formation than known cast reflectors. Use of improved reflector embodiments of the present invention in one or more dimensions makes it possible to avoid the use of collimator wires, thereby providing a beneficial cost savings. The elimination of collimator wires and use of potentially thinner reflectors allows use of detectors to acquire data representation of thinner slices in the z-direction. Laminates can be thinner than current cast materials and advantageously provide for more exposed scintillator.
- While the invention has been described in terms of various specific embodiments, those skilled in the art will recognize that the invention can be practiced with modification within the spirit and scope of the claims.
Claims (19)
1. A method for fabricating a detector array including a photosensor and scintillators, said method comprising the steps of:
placing a thermoplastically encased reflective film between the scintillators of a scintillator array; and
optically coupling the scintillators with the photosensor.
2. A method in accordance with claim I wherein the encased reflective film is prepared by positioning a reflective film within a thermoplastic closure and affixing said thermoplastic closure to the film.
3. A method in accordance with claim 2 wherein said step of affixing comprises laminating the thermoplastic closure to the reflective film.
4. A method in accordance with claim 2 , wherein the reflective film is encased in a process comprising depositing the reflective film directly on a thermoplastic sheet and laminating it with another layer of thermoplastic material.
5. A method in accordance with claim 2 wherein said reflective film is low x-ray damageable.
6. A photodetector array comprising:
an array of scintillators optically coupled to a photosensor array; and
a thermoplastically cased reflective film positioned between said scintillators of said array of scintillators.
7. The photodetector array of claim 6 , wherein said array is employed in a computed tomograph imaging system.
8. The photodetector array of claim 7 wherein said reflective film is thermoplastically encased in a process comprising depositing the reflective film directly on a thermoplastic sheet and laminating it with another layer of thermoplastic material.
9. The photodetector array of claim 8 wherein said reflective film is low x-ray damageable.
10. A computed tomograph imaging system comprising a rotating gantry, a radiation source, and a detector array on the rotating gantry configured to detect attentuated radiation from the radiation source passing through an object between the radiation source and the detector array, the detector array comprising a photosensor array, an array of scintillators, and a thermoplastically encased reflective film to said scintillator array, optically coupling said photosensor array to said scintillator array, said thermoplastically encased reflective film positioned between scintillators of said scintillator array.
11. The imaging system of Claim 10 wherein the object is a patient.
12. The imaging system of claim 10 wherein said reflective film is encased in a process comprising depositing the reflective film directly on a thermoplastic sheet and laminating it with another layer of thermoplastic material.
13. The imaging system of claim 10 wherein said reflective film is low x-ray damageable.
14. A method for detecting radiation in a radiation detection system including a radiation source, a detector array configured to detect attenuated radiation from the radiation source passing through an object between the radiation source and the detector array, the detector array including a photosensor array and an array of scintillators optically coupled to the photosensor array and a thermoplastically encased reflective film between the scintillators of the scintillator array, said method comprising the steps of:
emitting radiation directed at the object;
reflecting light from the thermoplastic reflective film and transmitting light generated by the scintillators to the photosensor array; and
generating an electrical output detection signal representative of light impacting the photosensor.
15. A method in accordance with claim 14 wherein the object is a patient.
16. A method in accordance with claim 14 wherein said reflective film is encased in a process comprising depositing the reflective film directly on a thermoplastic sheet and laminating it with another layer of thermoplastic material.
17. A method in accordance with claim 14wherein the reflective film is low x-ray damageable.
18. A method in accordance with claim 14 wherein the detection signal is fed to a DAS system.
19. A method in accordance with claim 14 wherein said reflective film is encased.
Priority Applications (4)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US09/751,872 US20020087073A1 (en) | 2000-12-29 | 2000-12-29 | CT detector reflector useful in detector scintillator array |
JP2001395609A JP2002328172A (en) | 2000-12-29 | 2001-12-27 | Ct detector-reflector useful in detector-scintillator array |
DE10164327A DE10164327A1 (en) | 2000-12-29 | 2001-12-28 | CT detector / reflector usable in a detector / scintillator arrangement |
US10/136,143 US6904304B2 (en) | 2000-12-29 | 2002-05-01 | CT detector reflector useful in detector scintillator array |
Applications Claiming Priority (1)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
US09/751,872 US20020087073A1 (en) | 2000-12-29 | 2000-12-29 | CT detector reflector useful in detector scintillator array |
Related Child Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US10/136,143 Continuation-In-Part US6904304B2 (en) | 2000-12-29 | 2002-05-01 | CT detector reflector useful in detector scintillator array |
Publications (1)
Publication Number | Publication Date |
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US20020087073A1 true US20020087073A1 (en) | 2002-07-04 |
Family
ID=25023872
Family Applications (2)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US09/751,872 Abandoned US20020087073A1 (en) | 2000-12-29 | 2000-12-29 | CT detector reflector useful in detector scintillator array |
US10/136,143 Expired - Fee Related US6904304B2 (en) | 2000-12-29 | 2002-05-01 | CT detector reflector useful in detector scintillator array |
Family Applications After (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
US10/136,143 Expired - Fee Related US6904304B2 (en) | 2000-12-29 | 2002-05-01 | CT detector reflector useful in detector scintillator array |
Country Status (3)
Country | Link |
---|---|
US (2) | US20020087073A1 (en) |
JP (1) | JP2002328172A (en) |
DE (1) | DE10164327A1 (en) |
Cited By (7)
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US20040032927A1 (en) * | 2002-08-15 | 2004-02-19 | Hoffman David Michael | Hybrid scintillator / photo sensor & direct conversion detector |
US20040102841A1 (en) * | 2000-01-31 | 2004-05-27 | Langberg Jonathan J. | Percutaneous mitral annuloplasty with cardiac rhythm management |
US7167539B1 (en) * | 2002-02-25 | 2007-01-23 | General Electric Company | Thermal sensing detector cell for a computed tomography system and method of manufacturing same |
US20100096777A1 (en) * | 2001-06-05 | 2010-04-22 | Appleby Michael P | Methods for Manufacturing Three-Dimensional Devices and Devices Created Thereby |
US8813824B2 (en) | 2011-12-06 | 2014-08-26 | Mikro Systems, Inc. | Systems, devices, and/or methods for producing holes |
US20140291528A1 (en) * | 2011-06-28 | 2014-10-02 | Carestream Health, Inc. | Radiation sensing thermoplastic composite panels |
US9206309B2 (en) | 2008-09-26 | 2015-12-08 | Mikro Systems, Inc. | Systems, devices, and/or methods for manufacturing castings |
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US7166849B2 (en) * | 2004-08-09 | 2007-01-23 | General Electric Company | Scintillator array for use in a CT imaging system and method for making the scintillator array |
JP2007125086A (en) * | 2005-11-01 | 2007-05-24 | Ge Medical Systems Global Technology Co Llc | X-ray detector and x-ray ct apparatus |
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US9206309B2 (en) | 2008-09-26 | 2015-12-08 | Mikro Systems, Inc. | Systems, devices, and/or methods for manufacturing castings |
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US10207315B2 (en) | 2008-09-26 | 2019-02-19 | United Technologies Corporation | Systems, devices, and/or methods for manufacturing castings |
US20140291528A1 (en) * | 2011-06-28 | 2014-10-02 | Carestream Health, Inc. | Radiation sensing thermoplastic composite panels |
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Also Published As
Publication number | Publication date |
---|---|
JP2002328172A (en) | 2002-11-15 |
DE10164327A1 (en) | 2002-08-22 |
US6904304B2 (en) | 2005-06-07 |
US20020123683A1 (en) | 2002-09-05 |
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Owner name: GE MEDICAL SYSTEMS GLOBAL TECHNOLOGY COMPANY, LLC, Free format text: ASSIGNMENT OF ASSIGNORS INTEREST;ASSIGNOR:HOFFMAN, DAVID M.;REEL/FRAME:011981/0563 Effective date: 20010426 |
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