U.S. patent application number 13/928462 was filed with the patent office on 2016-03-03 for scintillating material and related spectral filter.
The applicant listed for this patent is Norbert CONRADS, Simha LEVENE, Cornelis RONDA, Herbert SCHREINEMACHER, Guenter ZEITLER. Invention is credited to Norbert CONRADS, Simha LEVENE, Cornelis RONDA, Herbert SCHREINEMACHER, Guenter ZEITLER.
Application Number | 20160061962 13/928462 |
Document ID | / |
Family ID | 52114662 |
Filed Date | 2016-03-03 |
United States Patent
Application |
20160061962 |
Kind Code |
A9 |
RONDA; Cornelis ; et
al. |
March 3, 2016 |
SCINTILLATING MATERIAL AND RELATED SPECTRAL FILTER
Abstract
A host lattice modified GOS scintillating material and a method
for using a host lattice modified GOS scintillating material is
provided. The host lattice modified GOS scintillating material has
a shorter afterglow than conventional GOS scintillating material.
In addition, a radiation detector and an imaging device
incorporating a host lattice modified GOS scintillating material
are provided. A spectral filter may be used in conjunction with the
GOS scintillating material.
Inventors: |
RONDA; Cornelis; (Aachen,
DE) ; SCHREINEMACHER; Herbert; (Baesweller, DE)
; ZEITLER; Guenter; (Aachen, DE) ; CONRADS;
Norbert; (Raeren, DE) ; LEVENE; Simha; (D. N.
Hanegev, IL) |
|
Applicant: |
Name |
City |
State |
Country |
Type |
RONDA; Cornelis
SCHREINEMACHER; Herbert
ZEITLER; Guenter
CONRADS; Norbert
LEVENE; Simha |
Aachen
Baesweller
Aachen
Raeren
D. N. Hanegev |
|
DE
DE
DE
DE
IL |
|
|
Prior
Publication: |
|
Document Identifier |
Publication Date |
|
US 20150001398 A1 |
January 1, 2015 |
|
|
Family ID: |
52114662 |
Appl. No.: |
13/928462 |
Filed: |
June 27, 2013 |
Related U.S. Patent Documents
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Application
Number |
Filing Date |
Patent Number |
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13057483 |
Mar 9, 2011 |
8492724 |
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PCT/IB09/53056 |
Jul 14, 2009 |
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13928462 |
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61086826 |
Aug 7, 2008 |
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Current U.S.
Class: |
250/362 ;
250/361R; 250/363.01; 250/363.03; 250/363.04; 423/263 |
Current CPC
Class: |
C01P 2002/84 20130101;
G01T 1/2002 20130101; C01P 2002/54 20130101; C01F 17/294 20200101;
G01T 1/2985 20130101; G01T 1/202 20130101 |
International
Class: |
G01T 1/20 20060101
G01T001/20; C01F 17/00 20060101 C01F017/00; G01T 1/29 20060101
G01T001/29 |
Claims
1. A scintillating material comprising: a modified GOS material for
use with an imaging device, wherein no more than about 75% of the
gadolinium (Gd) of the GOS material is replaced with yttrium
(Y).
2. The scintillating material of claim 1, wherein the modified GOS
material is a ceramic.
3. The scintillating material of claim 2, wherein the modified GOS
material is a translucent ceramic.
4. (canceled)
5. The scintillating material of claim 4, wherein at most about 25%
of the gadolinium (Gd) is replaced with yttrium (Y).
6. The scintillating material of claim 5, wherein at most about 50%
of the gadolinium (Gd) is replaced with yttrium (Y).
7. (canceled)
8. The scintillating material of claim 1, wherein a portion of the
gadolinium (Gd) is replaced with lanthanum (La).
9-11. (canceled)
12. The scintillating material of claim 1, wherein a portion of the
gadolinium (Gd) is replaced with lutetium (Lu).
13-15. (canceled)
16. A radiation detector comprising: a modified GOS material,
wherein no more than about 75% of the gadolinium (Gd) of the GOS
material is replaced with yttrium (Y); and a photodetector
optically coupled to the modified GOS material.
17. The radiation detector of claim 16, wherein the radiation
detector detects x-rays.
18. The radiation detector of claim 16, wherein the modified SOS
material is a ceramic.
19. The radiation detector of claim 18, wherein the modified GOS
material is a translucent ceramic.
20. (canceled)
21. The radiation detector of claim 16, wherein a portion of the
gadolinium (Gd) is replaced with lanthanum (La).
22. The radiation detector of claim 16, wherein a portion of the
gadolinium (Gd) is replaced with lutetium (Lu).
23. The radiation detector of claim 16, wherein the photodetector
is a photodiode or a photomultiplier.
24. The radiation detector of claim 16, further comprising a
spectral filter disposed in an optical path between the modified
SOS material and the photodetector and adapted to substantially
block infrared light emitted from the modified GOS material.
25. A method for detecting radiation comprising the steps of:
receiving radiation with a modified GOS material, wherein no more
than about 75% of the gadolinium (Gd) of the GOS material is
replaced with yttrium (Y) and wherein the modified GOS material
emits light in response to receiving said radiation; and detecting
the light emitted from the modified GOS material with a
photodetector.
26. (canceled)
27. The method of claim 25, wherein a portion of the gadolinium
(Gd) is replaced with lanthanum (La).
28. The method of claim 25, wherein a portion of the gadolinium
(Gd) is replaced with lutetium (Lu).
29. An imaging device comprising: at least one radiation source;
and at least one radiation detector comprising: a modified GOS
material, wherein no more than about 75% of the gadolinium (Gd) of
the GOS material is replaced with yttrium (Y); and a photodetector
optically coupled to the modified GOS material.
30. The imaging device of claim 29, wherein the imaging device is a
CT, SPECT or PET imaging device.
31-39. (canceled)
Description
[0001] The present application relates generally to the imaging
arts and more particularly to a scintillating material and a
spectral filter for use with the scintillating material. The
application subject matter finds particular use with x-ray based
imaging systems, especially computed tomography (CT) imaging
systems, and will be described with particular reference thereto.
However, it could also be used in connection with other imaging
systems, such as single-photon emission computed tomography (SPECT)
or positron emission tomography (PET) imaging systems.
[0002] Computed tomography (CT) imaging systems typically employ an
x-ray source that generates x-rays that traverse an examination
region. A subject arranged in the examination region interacts with
and absorbs a portion of the traversing x-rays. A radiation
detector is arranged opposite the x-ray source to detect and
measure intensities of the transmitted x-rays. The radiation
detector typically includes several pixels, with each pixel
including one or more blocks of scintillating material optically
coupled to a photodetector. The scintillating material produces
bursts of light, called scintillation events, in response to
x-rays. The photodetector, such as a photodiode or photomultiplier,
produces electrical signals indicative of the intensity of the
scintillation events.
[0003] The performance of a scintillating material depends on many
properties of the material, including for example its stopping
power, brightness, and afterglow. Regarding afterglow in
particular, a scintillator's afterglow is the persistence of
excited light beyond the main emission. Afterglow may result from
defects in the scintillator material, or impurities, or have other
causes. Generally speaking, it is desirable to reduce a
scintillator's afterglow. That is, an afterglow which is shorter in
time is preferred to an afterglow which is longer in time.
Similarly, an afterglow having a narrower wavelength spectrum is
preferred to an afterglow having a broader wavelength spectrum. A
smaller afterglow is advantageous because it increases the number
of scintillation events which may be detected in a given time
period, and also increases the temporal resolution of the
detector.
[0004] As already mentioned, undesirable scintillator afterglow can
result from impurities present in the scintillator material.
Manufacturing a suitable scintillator for commercial use in a
radiation detector is a complicated and expensive process. The
process begins with gathering or synthesizing the requisite raw
materials. The raw materials are typically processed to remove
impurities. Unfortunately, some impurities are difficult to remove
in a commercially or economically feasible manner. After the raw
materials are gathered and purified to the extent practicable, they
are then combined to form a scintillator. Crystalline scintillators
are often formed by melting the raw materials together in a molten
pool of material, which is then crystallized. Ceramic scintillators
are often formed by pressing techniques and high temperature heat
treatments, however, without melting the scintillator material. A
scintillator may also be a composite material, comprising a mixture
of a scintillating powder dispersed within a host medium such as a
resin, wherein the scintillating powder and the host medium have a
similar index of refraction.
[0005] Conventionally, gadolinium oxysulfide (Gd.sub.2O.sub.2S)
(hereinafter "GOS") has been used as a scintillating material to
detect x-rays in CT systems. GOS has a high light output and short
afterglow in response to x-rays, in relation to many other
scintillating materials. However, GOS may often have Yb.sup.3+
impurities present, which can lead to undesirable afterglow as
discussed further below.
[0006] According to one aspect of the present invention, a host
lattice modified GOS scintillating material is provided. According
to another aspect of the present invention, a method of using a
host lattice modified GOS scintillating material is provided. In
yet additional aspects of the present invention, a radiation
detector and imaging device incorporating a host lattice modified
GOS scintillating material are provided. The host lattice modified
GOS scintillating material described herein has a shorter afterglow
than conventional GOS scintillating material while still providing
a relatively high light yield. Numerous additional advantages and
benefits will become apparent to those of ordinary skill in the art
upon reading the following detailed description of the preferred
embodiments.
[0007] According to a further aspect of the present invention, a
spectral filter is provided to reduce or substantially eliminate an
unwanted portion of light produced by a scintillator. Such a filter
may be used to reduce the effects of afterglow from the
scintillator, such the Yb.sup.3+ caused afterglow which may be
present in a conventional GOS scintillating material or a host
lattice modified GOS scintillating material.
[0008] The invention may take form in various chemical
compositions, various components and arrangements of components,
and in various process operations and arrangements of process
operations. The drawings are only for the purpose of illustrating
preferred embodiments and are not to be construed as limiting the
invention.
[0009] FIG. 1 is an exemplary CT imaging system, with a portion of
the stationary gantry cut away to reveal the rotating gantry, x-ray
source and radiation detector;
[0010] FIG. 2 is a close up view of a portion of the scintillating
material and one photodetector of the CT imaging system of FIG.
1;
[0011] FIG. 3 compares a portion of the emission spectra of two GOS
samples, one containing Yb impurities and the other lacking Yb
impurities; and
[0012] FIG. 4 is close up view of a portion of a scintillating
material and one photodetector of a CT imaging system, with an
optional spectral filter.
[0013] The medical imaging system and apparatus of the present
application is generally any medical imaging system, for example, a
CT, SPECT or PET imaging system. More specifically, with reference
to FIG. 1, in an exemplary embodiment, the medical imaging system
100 is a CT imaging system. The CT imaging system 100 includes a
subject support 110, such as a table or couch, which supports and
positions a subject being examined andor imaged, such as a patient.
The CT imaging system 100 includes a stationary gantry 120 with a
rotating gantry 130 mounted inside. A scanning tube 140 extends
through the stationary gantry 120. The scanning tube 140 defines an
examination region. The subject support 110 is linearly movable
along a Z-axis relative to the scanning tube 140, thus allowing the
subject support 110 and the imaged subject when placed thereon to
be moved within and removed from the scanning tube 140.
[0014] The rotating gantry 130 is adapted to rotate around the
scanning tube 140 (i.e., around the Z-axis) and the imaged subject
when located therein. One or more x-ray sources 150 with
collimator(s) 160 are mounted on the rotating gantry 130 to produce
an x-ray beam directed through the scanning tube 140 and the imaged
subject when located therein.
[0015] One or more radiation detector units 170 are also mounted on
the rotating gantry 130. Typically, the x-ray source(s) 150 and the
radiation detector unit(s) 170 are mounted on opposite sides of the
rotating gantry 130 from one another and the rotating gantry 130 is
rotated to obtain an angular range of projection views of the
imaged subject. The radiation detector unit(s) 170 include a
scintillating material 180. The scintillating material 180 may be,
for example, a ceramic scintillating material. In some embodiments,
the scintillating material 180 is a translucent ceramic. In some
embodiments, the scintillating material 180 is made up of an array
of individual crystals that are assembled together or cut from a
common scintillator plate by photoetching or some other
technique.
[0016] The CT imaging system 100 may include a grid 182, such as an
anti-scatter grid, which is arranged on a radiation receiving face
of the scintillating material 180. An array 190 of photodetectors
192, such as photodiodes or photomultipliers, is provided on the
opposite side of the scintillating material 180 from the grid 182.
Each of the photodetectors 192 is independently responsive to the
scintillation events that occur in the corresponding section 184 of
the scintillating material 180.
[0017] A computer (not shown) controls the operation of the CT
imaging system 100, including the operation of the subject support
110 and rotating gantry 130. The data acquired by the detector
unit(s) 170 is reconstructed to form an image that can optionally
be displayed on the computer, using conventional methods.
[0018] Referring now to FIG. 2, a close up view of a portion of the
scintillating material 180 and one photodetector 192 is shown. The
scintillating material 180 may be a GOS material with host lattice
modifications. The host lattice modifications shorten the time
duration of the afterglow with respect to conventional GOS
material. The GOS material of the present invention is also doped
with a doping agent. Some specific, non-limiting examples of doping
agents that can be used are cerium (Ce) and praseodymium (Pr).
Certain exemplary embodiments of the GOS material of the present
invention may be doped with both cerium and praseodymium. For
example, the GOS material may be doped with Pr.sup.+ concentrations
between 100 and 1000 mole ppm andor Ce.sup.+ concentrations between
0 and 50 mole ppm. However, different suitable doping agents may
also be used.
[0019] The GOS material with host lattice modifications can be
produced and used in the same manner as conventional GOS material.
Wafer, blank and array production can be performed using the same
equipment as used in conventional GOS production.
[0020] In various embodiments of the GOS material of the present
invention, the GOS host lattice is modified by substituting
yttrium, lanthanum andor lutetium, or combinations thereof, for a
portion of the gadolinium. For example, 25%, 50% or 75% or some
other percentage of the gadolinium may be replaced by either
yttrium, lanthanum andor lutetium, or combinations thereof. TABLE 1
below reports the results of afterglow testing of such host lattice
modified GOS samples which were doped with praseodymium and cerium.
Each of the various modified GOS samples set forth in TABLE 1 are
doped with approximately 700 mole ppm Pr.sup.3+ and approximately
10 mole ppm Ce.sup.3+. For comparison purposes, the same tests were
applied to two conventional GOS samples, without any host lattice
modifications, which were similarly doped.
TABLE-US-00001 TABLE 1 Photodiode [ppm] Photomultiplier [ppm]
Composition 5 ms 500 ms 2.1 s 5 ms 500 ms 2.1 s
(Gd.sub.0.75Y.sub.0.25).sub.2O.sub.2S:Pr;Ce 648 .+-. 44 59 .+-. 2
18 .+-. 1 492 .+-. 36 49 .+-. 2 16 .+-. 1
(Gd.sub.0.5Y.sub.0.5).sub.2O.sub.2S:Pr;Ce 962 .+-. 41 43 .+-. 2 15
.+-. 1 718 .+-. 43 33 .+-. 3 11 .+-. 1
(Gd.sub.0.25Y.sub.0.75).sub.2O.sub.2S:Pr;Ce 1195 .+-. 4 46 .+-. 4
13 .+-. 1 871 .+-. 57 34 .+-. 6 10 .+-. 1
(Gd.sub.0.75La.sub.0.25).sub.2O.sub.2S:Pr;Ce 1054 .+-. 6 5 .+-. 2 1
.+-. 1 955 .+-. 67 4 .+-. 3 2 .+-. 2
(Gd.sub.0.5La.sub.0.5).sub.2O.sub.2S:Pr;Ce 741 .+-. 33 8 .+-. 2 1
.+-. 1 643 .+-. 39 6 .+-. 2 1 .+-. 1
(Gd.sub.0.25La.sub.0.75).sub.2O.sub.2S:Pr;Ce 1681 .+-. 5 46 .+-. 6
10 .+-. 2 1542 .+-. 81 41 .+-. 7 9 .+-. 3
(Gd.sub.0.75Lu.sub.0.25)2O.sub.2S:Pr;Ce 1820 .+-. 6 79 .+-. 3 22
.+-. 1 465 .+-. 40 19 .+-. 2 4 .+-. 1
(Gd.sub.0.5Lu.sub.0.5).sub.2O.sub.2S:Pr;Ce 1804 .+-. 1 125 .+-. 4
38 .+-. 1 162 .+-. 34 16 .+-. 3 3 .+-. 2
(Gd.sub.0.25Lu.sub.0.75).sub.2O.sub.2S:Pr;Ce 4467 .+-. 3 279 .+-.
32 77 .+-. 9 511 .+-. 54 18 .+-. 2 5 .+-. 1 Gd.sub.2O.sub.2S:Pr;Ce
1495 .+-. 4 242 .+-. 11 51 .+-. 3 1026 .+-. 50 171 .+-. 8 41 .+-. 2
Gd.sub.2O.sub.2S:Pr;Ce 1119 .+-. 4 246 .+-. 15 46 .+-. 6 941 .+-.
28 208 .+-. 11 36 .+-. 2
[0021] As can be seen, the afterglow of the samples was separately
measured with a photodiode and with a photomultiplier. First, a
tested sample was exposed to a standard x-ray source for a standard
amount of time to cause the sample to luminesce. The x-ray source
was then shut off or removed. The sample's brightness or intensity
was then measured at 5 milliseconds, 500 milliseconds, and 2.1
seconds after removal of the x-ray source. The intensity values
reported in the table are in parts per million relative to a unit
of 1, which represents the initial intensity of the sample when the
x-ray source was removed.
[0022] Thus, for example, after 5 milliseconds the intensity of
(Gd.sub.0.75Y.sub.0.25).sub.2O.sub.2S:Pr;Ce as measured with a
photodiode was reduced to about 0.000648 of its original value. In
contrast, after 5 milliseconds the intensities of the two
conventional GOS samples as measured with the photodiode were
respectively reduced only to about 0.001495 and 0.001119 of their
original values. So, the afterglow of that modified GOS sample was
substantially less than the afterglow of the conventional GOS after
5 milliseconds.
[0023] TABLE 1 above thus illustrates the reduction of the
afterglow intensity of various compositions of GOS material with
host lattice modifications as compared to conventional GOS
material. Each of the host lattice modified GOS samples exhibited a
shorter afterglow time than conventional GOS material, except for
the lutetium GOS samples as measured by the photodiode. It is
believed that the disparity in those samples is due to the
contamination of Lu.sub.2O.sub.3 with Yb.sub.2O.sub.3 in the raw
materials used to generate the modified GOS. That contamination
leads to ytterbium (Yb.sup.3+) impurities in the resulting modified
GOS scintillator, and that impurity can increase the afterglow in
conventional GOS as well as host lattice modified GOS.
[0024] For example, FIG. 3 compares the emission spectra of a first
conventional GOS sample 302 containing Yb.sup.3+ impurities on the
order of a few parts per million, and a second conventional GOS
sample 304 from which substantially all Yb.sup.3+ impurities have
been removed. The main and desired spectrum is green-red visible
light, and is present in both samples. However, as can be seen, the
Yb.sup.3+ impurities lead to a significantly greater emission of
the first conventional GOS sample 302 in the infrared region,
between about 940 and 1100 nm. Unfortunately, manufacturing GOS as
pure as the second sample 304 reflected in FIG. 3 can be expensive,
especially in commercially significant quantities.
[0025] Turning back to TABLE 1, it can be seen that the
photomultiplier was much less sensitive to the longer afterglow of
the lutetium-modified GOS samples than the photodiode was. The
photomultiplier used a cut-off wavelength of 800 nm as an upper
limit, so it measured only wavelengths below infrared light. The
photodiode, on the other hand, also measured infrared light. Thus
the infrared region afterglow resulting from Yb.sup.3+ impurities
explains the disparity between the photomultiplier results (which
did not measure infrared light) and the photodiode results (which
measured infrared light).
[0026] To improve the performance of GOS--such as for example the
lutetium-modified GOS as measured with a photodiode--a spectral
filter may be employed. As shown in FIG. 4, a spectral filter 194
may be placed in the optical path between a scintillator material
180 and a photodetector 192. The spectral filter 194 operates to
remove an undesired portion of the scintillator material emission
while transmitting a desired part of the scintillator material
emission. For example, when the scintillator material is GOS, the
spectral filter 194 may transmit wavelengths below about 900 nm
(including the desired green-red light) while blocking out higher
wavelengths (including the undesired infrared light). Such short
wavelength pass filters may be produced by deposition of
transparent layers with alternating low and high refractive
indexes.
[0027] A spectral filter 194 may be inserted in the optical path
between a scintillator material 180 and a photodetector 192 in a
variety of manners, such as the following representative examples.
Conventional detectors often have a layer of optical cement
disposed between the scintillator material 180 and the
photodetector 192, in order to firmly hold the two components
together and transmit light from the scintillator 180 to the
photodetector 192. The spectral filter 194 may be placed within
such a layer of optical cement. As another alternative,
conventional systems also often have an optical coating on the
photodetector 192 to enhance the sensitivity spectrum of the
photodetector 192. The spectral filter 194 may be formed from
additional coating(s) placed on the photodetector 192.
[0028] As yet another alternative particularly suited to a
composite scintillator material, a small amount of a soluble light
absorber or dye may be incorporated within the host medium. The
light absorber acts as a filter by absorbing the undesired spectra
and not absorbing the desired spectra. Preferably, the light
absorber is sufficiently radiation hard.
[0029] The spectral filter 194 may take many forms. For example, it
may be an absorbing filter which absorbs the undesired afterglow
light. As another example, the spectral filter 194 may be a
reflecting filter which reflects the undesired afterglow light.
Many types of filters are known which would be suitable for this
application, such as glass filters, interference filters,
diffraction grating filters, prisms, and the like.
[0030] The invention has been described with reference to the
preferred embodiments. Obviously, modifications and alterations
will occur to others upon reading and understanding the preceding
detailed description. It is intended that the invention be
construed as including all such modifications and alterations
insofar as they come within the scope of the appended claims or the
equivalents thereof. The invention may take form in various
chemical compositions, components and arrangements, combinations
and sub-combinations of the elements of the disclosed
embodiments.
* * * * *