WO2002037139A1 - Scintillateur base sur un appareil de detection et procede utilisant une matrice bidimensionnelle d'elements de detection de lumiere - Google Patents

Scintillateur base sur un appareil de detection et procede utilisant une matrice bidimensionnelle d'elements de detection de lumiere Download PDF

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Publication number
WO2002037139A1
WO2002037139A1 PCT/SE2001/002377 SE0102377W WO0237139A1 WO 2002037139 A1 WO2002037139 A1 WO 2002037139A1 SE 0102377 W SE0102377 W SE 0102377W WO 0237139 A1 WO0237139 A1 WO 0237139A1
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WO
WIPO (PCT)
Prior art keywords
light
layer
radiation
scintillating layer
scintillating
Prior art date
Application number
PCT/SE2001/002377
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English (en)
Inventor
Tom Francke
Leif Ericsson
Original Assignee
Xcounter Ab
Priority date (The priority date is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the date listed.)
Filing date
Publication date
Application filed by Xcounter Ab filed Critical Xcounter Ab
Priority to EP01979193A priority Critical patent/EP1330664A1/fr
Priority to AU2002211178A priority patent/AU2002211178A1/en
Publication of WO2002037139A1 publication Critical patent/WO2002037139A1/fr

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Classifications

    • 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
    • G01T1/2018—Scintillation-photodiode combinations

Definitions

  • the present invention generally relates to apparatus and methods for detection of ionizing radiation, particularly but not exclusively X-rays, and is usable in a variety of fields including e.g. medical radiology, computerized tomography (CT), microscopy, and non-destructive testing.
  • ionizing radiation particularly but not exclusively X-rays
  • CT computerized tomography
  • microscopy microscopy
  • non-destructive testing e.g. medical radiology, computerized tomography (CT), microscopy, and non-destructive testing.
  • Scintillator based detection systems are widely used for high- resolution imaging of gamma and x-rays. Such imaging systems use the detected radiation to produce a signal, which can be used to operate a visual display, such as a cathode ray tube.
  • U.S. Pat. No. 5,144,141 One example of such radiation detector is disclosed in U.S. Pat. No. 5,144,141.
  • radiation incident on the detector passes through a collimator and strikes a scintillator, which is divided into a plurality of scintillator elements arranged in rows and columns.
  • An array of internal photodetectors divided into rows and columns are optically connected to the scintillator elements .
  • Each photodetector is electrically coupled to a respective detect and hold circuit which stores the pulse generated by the photodetector; the stored pulses are sampled via a multiplexed switching arrangement to allow the stored signal from each detect and hold circuit to be processed to produce a digitized imaging signal which corresponds to the energy level of, and location on the array of, the detected incident radiation.
  • the digitized imaging signal is supplied to display memory and analysis equipment for the device.
  • Improved spatial resolution requires the use of a large number of photodetectors and a scintillator system, which generates light photons only in the scintillator segment in which the incident radiation was absorbed.
  • the use of a larger number of photodetectors in a large array or to increase the resolution of the device rapidly results in very complex and expensive apparatus .
  • the spatial resolution is limited due to the facts that the incident radiation beam is divergent and that the scintillator has to be sufficiently deep (i.e. having a sufficient dimension in the direction of the incident radiation) to absorb a substantial portion of the incoming radiation.
  • the photons in a particular ray bundle of the radiation beam may get absorbed in different scintillator segments (if the segments are small) and consequently blur the image obtained.
  • the scintillator light is emitted isotropically and illuminates a large area of the photodetector, hence reducing the position resolution.
  • photodetectors are sensitive to direct irradiation by the incident X-rays and hence measures have to be taken in order to prevent the incident radiation from reaching the photodetectors .
  • collimators and a front and back wall define an array of volumes or detector cells wherein scintillator bodies are arranged.
  • Photo diodes are arranged on top of and underneath each detector cell aligned with the collimators such that light emitted in a scintillator body can be detected by a single one of the photo diodes (Fig. 1; column 4, lines 4-32).
  • a second embodiment comprises a scintillator body made of a single crystal or other homogenous scintillator material (Fig. 6; column 5, lines 40-47).
  • a further object of the invention is to provide such detection apparatus and method, which provide for high sensitivity, and can thus operate at very low X-ray fluxes.
  • Yet a further object of the present invention is to provide such detection apparatus and method wherein detection elements are arranged so as not to be exposed to direct irradiation by the ionizing radiation.
  • Still a further object of the invention is to provide such detection apparatus and method, wherein the isotropically emitted light is collimated to illuminate a smaller area of the detector arrangement to further improve the spatial resolution.
  • Yet a further object of the present invention is to provide such detection apparatus and method, which are effective, fast, accurate, reliable, and of low cost.
  • Such geometry provides for a very high detection efficiency as the absorption depth may be made large so as to absorb a major portion of the incoming radiation.
  • An improved spatial resolution is obtained as the perpendicular detection is parallax-free.
  • the light collection as well as the spatial resolution in the inventive detector geometry is improved as the distance between the absorption/interaction region and the detecting elements may be made very short.
  • the detector may be made very thin (from bottom to top), which provides for the stacking of a plurality of detectors to provide a multi-line detector configuration.
  • the homogenous scintillator layer together with the two- dimensional matrix of light detecting elements enable the use of radiation sources of any divergence, and the arrangement of the detector at any distance from the radiation source, and still being able to perform one-dimensional imaging, and optionally spectrally resolved measurement. It is just a matter of using a single line of light detecting elements transverse to the incident radiation, or if larger signals are wanted, grouping light detecting elements along lines pointing towards the radiation source.
  • one-dimensional imaging may be performed, and by providing a plurality of detecting elements in the direction of the incident radiation beam energy resolved measurements are capable of being performed.
  • Fig. 1 illustrates schematically, in a cross-sectional side view, a scintillator based detection apparatus according to a preferred embodiment of the present invention.
  • Fig. 2 illustrates schematically, in a cross sectional top view, the detection apparatus of Fig. 1.
  • Figs. 3a and 3b illustrate schematically, in cross-sectional side views, portions of scintillator based detection apparatus according to two preferred embodiments of the present invention, wherein the spatial resolution obtainable is clearly indicated.
  • Fig. 4 illustrates schematically, in a front view with collimator portions cut-away, a scintillator based detection apparatus according to a further preferred embodiment of the present invention.
  • FIGs. 1 and 2 which schematically, in cross- sectional side and top views, respectively, illustrate a scintillator based detection apparatus, a preferred embodiment of the present invention will be depicted.
  • the detection apparatus comprises a scintillator 3, the front surface 3a of which being directed towards a planar beam 5 of ionizing radiation to be measured.
  • the scintillator 3 may comprise a solid scintillating substance, a liquid scintillating substance, e.g. liquid xenon or argon, or a scintillating gas, e.g. xenon or argon.
  • the scintillator 3 is formed of a material having a relatively high efficiency for converting the incident radiation to optical energy, a relatively fast decay constant, and good optical transparency.
  • Cesium iodide has proven to be a good scintillator material for the detection of x-rays, having high conversion efficiency, a decay constant of 1 microsecond, and a refractive index of 1.8.
  • other known scintillator materials such as for instance Nal, BaF2 or polymeric materials, may be used in the scintillator of the present invention.
  • the scintillator 3 is made of a single relatively scintillator homogenous material, such as e.g. a scintillator body made from a single crystal.
  • Collimator 7 is typically of lead or tungsten, and the radiation entrance can be divided into a plurality of entrance openings 9 arranged along a line (Fig. 2), but optionally a single elongated slit opening is provided (not illustrated in Figs . 1 and 2 ) .
  • a light-absorbing layer 11 is covering top surface 3b of the scintillator 3.
  • layer 11 is light reflective.
  • a patterned, grid-like layer 13 is provided at bottom surface 3c of scintillator 3, which bottom layer thus define a two-dimensional matrix of openings 15 through there.
  • the space in openings 15 may be filled by any suitable light transparent or scintillating material (e.g. same material as in scintillator 3).
  • the layer 13 may be of a light-absorbing or at least partly of a light-reflecting material.
  • a light detection arrangement 16 for detection of light.
  • Arrangement 16 comprises typically a plurality of light detecting elements 17 arranged in a two- dimensional matrix on a substrate 19.
  • Arrangement 16 is aligned with layer 13 such that the respective openings 15 are overlying respective light detecting elements 17.
  • the light detecting elements 17 may be photodiodes, photosensitive TFT's, photodiode based amplifiers, CCD elements, or other photon counting or light integrating detecting elements .
  • the light detecting elements 17 may be arranged in a way to compensate for the divergence of any incoming radiation.
  • the read-out elements may be arranged in a fan-like configuration, wherein each of the elements is aiming at the radiation source of the incoming radiation.
  • the light detecting arrangement 16 is connected to a signal-processing device (not illustrated) for necessary and/or desired post-processing of collected signal data.
  • the read-out elements 17 are thus separately connected to the signal processing circuit by means of individual signal conduits.
  • a signal display unit (neither illustrated) is provided for displaying the processed signal data.
  • a detection element matrix may typically have a width of up to 50 cm and comprise many thousands of detection elements.
  • a small area array used for some applications may be smaller than 1 mm in width.
  • the detection apparatus of Figs. 1 and 2 is positioned in the path of radiation desired to be detected. Rays of incident radiation emanating directly from the subject under examination will travel in a path so as to pass through entrance openings 9 in collimator 7 and enter the scintillator 3, whereas unwanted radiation scattered from the subject under examination towards the detection device will typically travel at some angle to the plane of the collimator and thus will not be able to traverse any of the openings .
  • the radiation is preferably X-rays, but the invention is useful with any kind of ionizing radiation that a scintillator is capable of converting into light.
  • the energy level of the incident radiation ranges between about 10 keV and 500 keV.
  • typical interactions between the incident radiation and the scintillator material include photoelectric absorption and Compton scattering. Both of these processes result in electrons being emitted from atoms in the scintillator that are struck by the incident ray, and as these electrons pass through the scintillator material their energy is converted to visible radiant light energy.
  • the signals obtained by the light detecting elements 17 are subsequently post-processed and displayed.
  • a detection apparatus By using a transverse array (i.e. parallel with collimator 7) of light detecting elements 17 a detection apparatus is achieved, wherein photons derivable mainly from interactions with transversely separated portions of the planar radiation beam 5 are separately detectable.
  • one-dimensional imaging may be performed.
  • grouping light detecting elements which are located along the direction of the radiation beam 5, and providing a single measured value for each of these groups, an increased signal level and sensitivity may be obtained.
  • the depth within the scintillator where an interaction between a radiation photon and the scintillating material takes part is governed statistically by the absorption rate of the X- rays in the material used. High-energy X-rays will generally have a larger penetration depth than X-rays of lower energy.
  • the absorption depth may be made large so as to absorb a major portion of the incoming radiation, which provides for a very high detection efficiency.
  • an improved spatial resolution is obtained as the perpendicular detection is parallax-free.
  • the light collection in the inventive detector geometry is improved as the distance between the absorption/interaction region and the detecting elements may be made very short.
  • the detector may be made shorter (in the direction of the incident radiation) than a corresponding gaseous-based detector, which provides for easier alignment of the detector.
  • a detector length in the millimeter region may be used.
  • the detector may be made very thin (from bottom to top), which provides for the stacking of a plurality of detectors to provide a multi-line detector configuration.
  • a scintillator as thin as 10 ⁇ m may be employed.
  • the detection apparatus of Figs. 1 and 2 provides for good collimation capabilities of radiation beam 5, whereby images contain very small signals originating from scattered radiation within the detector. Thus, an increased signal-to- noise ratio in the images detected, may be obtained.
  • FIG. 3a and b schematically, in cross-sectional side views, illustrate portions of scintillator based detection apparatus, aspects on the grid-like layer 13/light detecting element matrix 17 combination of the present invention will be described.
  • the grid-like layer 13 is not very thick (i.e. having not a very large vertical dimension in Fig. 3a) and made of a light absorbing material.
  • light emitted from an interaction volume 23 as a result of absorption of a particular radiation photon 21 within a given angle ⁇ will pass through the opening 15 of the layer 13 and be detected by a single light detecting element 17a.
  • the angles are in fact solid angles or similar three-dimensional angle distributions.
  • the grid-like layer 13 is relatively thick and surfaces 13a thereof facing the respective openings 15 are made of a light-reflecting material.
  • surfaces 13a thereof facing the respective openings 15 are made of a light-reflecting material.
  • Preferred dimensions may for instance include a scintillator thickness (i.e. dimension from the light absorbing layer 11 to the grid-like layer 13) of between about 10 ⁇ m and about 3 mm, preferably between about 10 ⁇ m and about 1 mm; a collimator radiation entrance height (i.e. dimension limiting the thickness of a planar radiation beam enterable into the detector) preferably slightly smaller and located such that the radiation is propagating close to the grid-like layer 13), a grid-like layer thickness of between about 10 ⁇ m and about 1 mm, and gridlike layer opening widths of less than about 1 mm, preferably less than 100 ⁇ m, and more preferably between about 1 ⁇ m and about 50 ⁇ m.
  • a scintillator thickness i.e. dimension from the light absorbing layer 11 to the grid-like layer 13
  • a collimator radiation entrance height i.e. dimension limiting the thickness of a planar radiation beam enterable into the detector
  • a photocathode 41 is arranged adjacent scintillator 3, which is arranged such that it releases photoelectrons in dependence on the light photons that hit it.
  • the cathode shall be thin such that it is capable of releasing electrons from the surface opposite to the surface onto which the photons (e.g. those indicated by 25) are impinging.
  • An electron avalanche amplification arrangement is provided next to photocathode 41 preferably provided with two electrodes; a grid-like avalanche cathode 43 and an avalanche anode 45, and is adapted to collect photoelectrons released from photocathode and to strongly avalanche amplify these.
  • Geometries and amplification material of the light detecting arrangement and electric potentials, at which the photocathode and avalanche electrodes are held, are selected such that a suitable amplification is obtained.
  • electrical field lines between a single one of the read-out elements 45a and the photocathode 41 are schematically indicated in Fig. 4 by reference numeral 46.
  • a closed chamber 47 between the electrodes containing a gas suitable for electron avalanche amplification is provided.
  • suitable amplification media include for instance argon, C02 , ethane, and mixtures of argon and isobuthane.
  • liquid or solid electron amplification substances are used.
  • a dielectric 49 may be arranged between avalanche cathode 43 and avalanche anode 45. This could be a gas or a solid substrate carrying cathode 43 and anode 45.
  • the applied voltages produce a strong electric field in an array or a matrix of avalanche amplification regions 51.
  • the avalanche regions 51 are formed in a region between and around the edges of the avalanche cathode 43 which are facing each other, and between the avalanche cathode 43 and the avalanche anode 45.
  • light detecting arrangement comprises a read-out arrangement including a plurality of read-out elements arranged in an array or a matrix electrically insulated from each other, the read-out arrangement being adapted to detect pulses induced by the avalanche electrons and/or correspondingly produced ions .
  • the avalanche anode is patterned and constitutes read-out arrangement, but a separate read-out arrangement may be provided.
  • Read-out elements 45 are preferably individually connected to a signal-processing device (not illustrated) for necessary and/or desired post-processing of collected signal data.
  • a signal display unit (neither illustrated) is finally provided for displaying the processed signal data.
  • the openings 15 of the grid-like layer 13; the avalanche regions 51 and the anode/read-out elements are aligned and overlie each other.
  • light 25 emitted within a region 23 in the scintillator 3 will travel towards photocathode 41, pass an opening in the grid-like layer 13, hit the photocathode 41, and cause electrons, so called photoelectrons, to be emitted from the backside of the photocathode.
  • Such released electrons are then drifted towards the avalanche cathode and are accelerated (schematically indicated by arrow 53) due to the strong electric field between the avalanche cathode 43 and avalanche anode 45.
  • Such accelerated electrons will interact with other material (e.g. atoms, molecules etc.) within a single one 51a of the avalanche regions 51 and cause electron-ion pairs to be produced. Those produced electrons will also be accelerated in the field, and will interact repetitively with new materia, causing further electron-ion pairs to be produced.
  • This electron avalanche amplifying process continues during the travel of the electrons towards a single one 45a of the read-out elements 45. In such manner detection of high spatial resolution and high sensitivity may be performed.
  • the present invention thus incorporating the homogenous scintillator layer together with the light detection arrangement comprising a plurality of light detecting elements arranged in a two-dimensional matrix, enables the use of radiation sources of any divergence, and the arrangement of the detector at any distance from the radiation source, while still one-dimensional imaging, and optionally spectrally resolved measurement, are possible to perform. It is simply to use a single line of light detecting elements transverse to the incident radiation, or if larger signals are wanted, to group light detecting elements along lines pointing towards the radiation source.

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  • Physics & Mathematics (AREA)
  • Health & Medical Sciences (AREA)
  • Life Sciences & Earth Sciences (AREA)
  • General Physics & Mathematics (AREA)
  • High Energy & Nuclear Physics (AREA)
  • Molecular Biology (AREA)
  • Spectroscopy & Molecular Physics (AREA)
  • Measurement Of Radiation (AREA)

Abstract

L'invention concerne un détecteur de rayonnement comprenant une couche scintillante (3); une entrée de rayonnement (9); et un système de détection de lumière (16) comportant une matrice bidimensionnelle d'éléments de détection de lumière (17), le système de détection de lumière étant orienté par rapport à l'entrée de rayonnement de telle façon que la lumière (25) qui est émise dans la couche scintillante dans une direction sensiblement perpendiculaire à la direction avec laquelle le faisceau lumineux a pénétré dans la couche scintillante, puisse être détectée. En outre, une couche de type grille (13) comportant une pluralité d'ouvertures transparentes à la lumière (15) est placée entre la couche scintillante et le système de détection de lumière avec lequel il est aligné, de telle façon que les ouvertures transparentes à la lumière (15) respectives recouvrent les éléments de détection de lumière (17) respectifs.
PCT/SE2001/002377 2000-11-02 2001-10-30 Scintillateur base sur un appareil de detection et procede utilisant une matrice bidimensionnelle d'elements de detection de lumiere WO2002037139A1 (fr)

Priority Applications (2)

Application Number Priority Date Filing Date Title
EP01979193A EP1330664A1 (fr) 2000-11-02 2001-10-30 Scintillateur base sur un appareil de detection et procede utilisant une matrice bidimensionnelle d'elements de detection de lumiere
AU2002211178A AU2002211178A1 (en) 2000-11-02 2001-10-30 Scintillator based detection apparatus and method using two-dimensional matrix of light detecting elements

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
SE0004012A SE519875C2 (sv) 2000-11-02 2000-11-02 Scintillatorbaserad metod och detektor med två-dimensionell matris av detektorelement
SE0004012-1 2000-11-02

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EP (1) EP1330664A1 (fr)
AU (1) AU2002211178A1 (fr)
SE (1) SE519875C2 (fr)
WO (1) WO2002037139A1 (fr)

Cited By (2)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE102005025641A1 (de) * 2005-06-03 2006-12-07 MAX-PLANCK-Gesellschaft zur Förderung der Wissenschaften e.V. Srahlungsdetektor zur Detektion intensitätsarmer Strahlung
US20140264043A1 (en) * 2013-03-14 2014-09-18 Varian Medical Systems, Inc. X-ray imager with lens array and transparent non-structured scintillator

Citations (5)

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Publication number Priority date Publication date Assignee Title
FR2625331A1 (fr) * 1987-12-29 1989-06-30 Walter Jean Jacques Capteur matriciel pour rayons x et gamma
DE3827976A1 (de) * 1988-08-18 1990-02-22 Isotopenforschung Dr Sauerwein Roentgenstrahlungsbilddetektor und verfahren zu seiner herstellung
EP0637084A1 (fr) * 1993-07-29 1995-02-01 General Electric Company Détecteur de radiations à l'état solide ayant une couche d'arrêt
US5539206A (en) * 1995-04-20 1996-07-23 Loral Vought Systems Corporation Enhanced quantum well infrared photodetector
US6167110A (en) * 1997-11-03 2000-12-26 General Electric Company High voltage x-ray and conventional radiography imaging apparatus and method

Family Cites Families (1)

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Publication number Priority date Publication date Assignee Title
US4303860A (en) * 1979-07-30 1981-12-01 American Science And Engineering, Inc. High resolution radiation detector

Patent Citations (5)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
FR2625331A1 (fr) * 1987-12-29 1989-06-30 Walter Jean Jacques Capteur matriciel pour rayons x et gamma
DE3827976A1 (de) * 1988-08-18 1990-02-22 Isotopenforschung Dr Sauerwein Roentgenstrahlungsbilddetektor und verfahren zu seiner herstellung
EP0637084A1 (fr) * 1993-07-29 1995-02-01 General Electric Company Détecteur de radiations à l'état solide ayant une couche d'arrêt
US5539206A (en) * 1995-04-20 1996-07-23 Loral Vought Systems Corporation Enhanced quantum well infrared photodetector
US6167110A (en) * 1997-11-03 2000-12-26 General Electric Company High voltage x-ray and conventional radiography imaging apparatus and method

Non-Patent Citations (1)

* Cited by examiner, † Cited by third party
Title
See also references of EP1330664A1 *

Cited By (4)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
DE102005025641A1 (de) * 2005-06-03 2006-12-07 MAX-PLANCK-Gesellschaft zur Förderung der Wissenschaften e.V. Srahlungsdetektor zur Detektion intensitätsarmer Strahlung
US7847230B2 (en) 2005-06-03 2010-12-07 Max-Planck-Gesellschaft Zur Foerderung Der Wissenschaften E.V. Radiation detector for detecting low-intensity radiation by means of avalanche amplification
US20140264043A1 (en) * 2013-03-14 2014-09-18 Varian Medical Systems, Inc. X-ray imager with lens array and transparent non-structured scintillator
US9606244B2 (en) * 2013-03-14 2017-03-28 Varex Imaging Corporation X-ray imager with lens array and transparent non-structured scintillator

Also Published As

Publication number Publication date
SE0004012D0 (sv) 2000-11-02
SE0004012L (sv) 2002-05-03
AU2002211178A1 (en) 2002-05-15
EP1330664A1 (fr) 2003-07-30
SE519875C2 (sv) 2003-04-15

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