U.S. patent application number 15/262102 was filed with the patent office on 2017-03-30 for radiation imaging apparatus and method of controlling radiation imaging apparatus.
The applicant listed for this patent is CANON KABUSHIKI KAISHA. Invention is credited to Kentaro Fujiyoshi, Kazuya Furumoto, Jun Kawanabe, Masato Ofuji, Minoru Watanabe, Hiroshi Wayama, Keigo Yokoyama.
Application Number | 20170090041 15/262102 |
Document ID | / |
Family ID | 58407034 |
Filed Date | 2017-03-30 |
United States Patent
Application |
20170090041 |
Kind Code |
A1 |
Yokoyama; Keigo ; et
al. |
March 30, 2017 |
RADIATION IMAGING APPARATUS AND METHOD OF CONTROLLING RADIATION
IMAGING APPARATUS
Abstract
A radiation imaging apparatus is provided. The apparatus
comprises first pixels arranged in an image sensing region to
obtain a radiation image, a second pixel configured to obtain a
dose of incident radiation and a control unit configured to control
the first pixels and the second pixel. The control unit causes the
first pixels to accumulate charge corresponding to a radiation
dose, while causing the second pixel to operate in a detection
cycle determined based on irradiation information of radiation
before irradiation with radiation, obtains a dose of incident
radiation for each detection cycle, and corrects the obtained
radiation dose in accordance with an amount of noise output from
the second pixel operating in the detection cycle.
Inventors: |
Yokoyama; Keigo; (Honjo-shi,
JP) ; Watanabe; Minoru; (Yokohama-shi, JP) ;
Ofuji; Masato; (Takasaki-shi, JP) ; Kawanabe;
Jun; (Kawasaki-shi, JP) ; Fujiyoshi; Kentaro;
(Tokyo, JP) ; Wayama; Hiroshi; (Kawasaki-shi,
JP) ; Furumoto; Kazuya; (Tokyo, JP) |
|
Applicant: |
Name |
City |
State |
Country |
Type |
CANON KABUSHIKI KAISHA |
Tokyo |
|
JP |
|
|
Family ID: |
58407034 |
Appl. No.: |
15/262102 |
Filed: |
September 12, 2016 |
Current U.S.
Class: |
1/1 |
Current CPC
Class: |
G01T 1/023 20130101;
G01T 1/17 20130101; G01T 1/2018 20130101; H04N 5/32 20130101 |
International
Class: |
G01T 1/17 20060101
G01T001/17; G01T 1/20 20060101 G01T001/20; G01T 1/02 20060101
G01T001/02 |
Foreign Application Data
Date |
Code |
Application Number |
Sep 28, 2015 |
JP |
2015-190335 |
Claims
1. A radiation imaging apparatus comprising: a plurality of first
pixels arranged in an image sensing region to obtain a radiation
image; a second pixel configured to obtain a dose of incident
radiation during irradiation with radiation; and a control unit
configured to control the plurality of first pixels and the second
pixel, wherein the control unit causes the plurality of first
pixels to accumulate electric charge corresponding to a radiation
dose, while causing the second pixel to operate in a detection
cycle determined based on irradiation information of radiation
before irradiation with radiation, obtains a dose of incident
radiation for each detection cycle, and corrects the obtained
radiation dose in accordance with an amount of noise output from
the second pixel operating in the detection cycle.
2. The apparatus according to claim 1, wherein the control unit
further configured to, stops irradiation with radiation based on a
radiation dose after correction, and reads out electric charge
accumulated in the plurality of first pixels after irradiation with
radiation.
3. The apparatus according to claim 1, wherein the irradiation
information includes information of irradiation time of radiation,
and the control unit determines the detection cycle based on the
irradiation time.
4. The apparatus according to claim 3, wherein the control unit
calculates the detection cycle by dividing the irradiation time by
a predetermined count.
5. The apparatus according to claim 3, wherein the control unit
determines the detection cycle based on a lookup table indicating a
relationship between irradiation times and detection cycles.
6. The apparatus according to claim 1, wherein the second pixel
includes a detecting element configured to obtain a dose of
incident radiation during irradiation with radiation, the
irradiation information includes information concerning a dose of
radiation with which the radiation imaging apparatus is irradiated,
and the control unit determines an estimated radiation dose of
radiation incident on the detecting element in a predetermined
period in accordance with the information concerning radiation
dose, and determines the detection cycle based on the estimated
radiation dose.
7. The apparatus according to claim 1, further comprising a memory
unit storing an image sensing condition, wherein the control unit
compares the irradiation information with the image sensing
condition and determines the detection cycle based on the image
sensing condition including the irradiation information.
8. The apparatus according to claim 1, wherein the irradiation
information includes information of the number of first pixels, of
the plurality of first pixels, which are used to form one pixel of
the radiation image, and the control unit determines the detection
cycle based on the number of first pixels which are used to form
one pixel.
9. The apparatus according to claim 1, wherein the control unit
causes, before irradiation with radiation, the second pixel to
operate in the detection cycle determined based on the irradiation
information and uses a signal value output from the second pixel as
the amount of noise.
10. The apparatus according to claim 9, wherein the control unit
obtains the plurality of signal values output from the second pixel
in the detection cycle and uses an average value of the plurality
of obtained signal values as the amount of noise.
11. The apparatus according to claim 1, further comprising a noise
amount memory unit storing each signal value output from the second
pixel when the second pixel is made to operate in a plurality of
detection cycles without irradiation with radiation, wherein the
control unit determines the amount of noise by using the respective
signal value in accordance with the detection cycle determined
based on the irradiation information.
12. The apparatus according to claim 1, wherein when the control
unit fails to determine at least one of the detection cycle or the
amount of noise, the apparatus does not perform irradiation with
radiation.
13. The apparatus according to claim 1, wherein the irradiation
information includes a target radiation dose of radiation incident
on the second pixel, and the control unit outputs a stop
determination signal for stopping irradiation with radiation to a
radiation source configured to irradiate the radiation imaging
apparatus with radiation when the radiation dose after the
correction has reached the target radiation dose or is expected to
reach the target radiation dose.
14. The apparatus according to claim 13, wherein the irradiation
information includes an upper limit of radiation irradiation time,
and the control unit outputs a stop determination signal for
stopping irradiation with radiation to the radiation source when
the radiation irradiation time has reached the upper limit before
the radiation dose after the correction reaches the target
radiation dose or is expected to reach the target radiation
dose.
15. The apparatus according to claim 1, wherein the detection cycle
is a constant cycle during irradiation with radiation.
16. The apparatus according to claim 1, wherein the plurality of
first pixels include a plurality of conversion elements arranged in
an image sensing region to obtain a radiation image, and the second
pixel is arranged in the image sensing region.
17. A radiation imaging system comprising: a radiation imaging
apparatus defined in claim 1; and a signal processing unit
configured to process a signal from the radiation imaging
apparatus.
18. A method of controlling a radiation imaging apparatus including
a plurality of first pixels arranged in an image sensing region to
obtain a radiation image, and a second pixel configured to obtain a
dose of incident radiation during irradiation with radiation, the
method comprising: causing the plurality of first pixels to
accumulate electric charge corresponding to a radiation dose; while
causing the second pixel to operate in a detection cycle determined
based on irradiation information of radiation before irradiation
with radiation, obtaining a dose of incident radiation for each
detection cycle; and correcting the obtained radiation dose in
accordance with an amount of noise output from the second pixel
operating in the detection cycle.
19. A program stored in a non-transitory storage medium for causing
a computer to execute a method of controlling a radiation imaging
apparatus including a plurality of first pixels arranged in an
image sensing region to obtain a radiation image, and a second
pixel configured to obtain a dose of incident radiation during
irradiation with radiation, the method comprising: causing the
plurality of first pixels to accumulate electric charge
corresponding to a radiation dose; while causing the second pixel
to operate in a detection cycle determined based on irradiation
information of radiation before irradiation with radiation,
obtaining a dose of incident radiation for each detection cycle;
and correcting the obtained radiation dose in accordance with an
amount of noise output from the second pixel operating in the
detection cycle.
Description
BACKGROUND OF THE INVENTION
[0001] Field of the Invention
[0002] The present invention relates to a radiation imaging
apparatus, and a method of controlling the radiation imaging
apparatus.
[0003] Description of the Related Art
[0004] A radiation imaging apparatus has been widely used, which
includes a pixel array including a two-dimensional array of pixels
each obtained by combining a conversion element which converts
radiation into electric charge and a switch element such as a TFT
(Thin-Film Transistor). Such a radiation imaging apparatus is known
to have an AEC (Automatic Exposure Control) function. The AEC
function detects the dose of radiation incident on the radiation
imaging apparatus during irradiation with radiation. Japanese
Patent Laid-Open No. 2014-219248 discloses a technique of changing
a detection cycle in accordance with an incident radiation dose
during irradiation with radiation.
SUMMARY OF THE INVENTION
[0005] As the dose of radiation incident on a radiation imaging
apparatus decreases, a signal amount obtained by conversion from
the incident radiation also decreases. A reduction in signal amount
may decrease the S/N ratio of radiation amount detection and
increase the influence of noise output from each pixel for
detecting a radiation dose. Japanese Patent Laid-Open No.
2014-219248 discloses nothing about the influence of noise output
from each pixel for detecting a radiation dose.
[0006] Some embodiments of the present invention provide a
technique of more accurately detecting the dose of radiation
incident on a radiation imaging apparatus.
[0007] According to some embodiments, a radiation imaging apparatus
comprising: a plurality of first pixels arranged in an image
sensing region to obtain a radiation image; a second pixel
configured to obtain a dose of incident radiation during
irradiation with radiation; and a control unit configured to
control the plurality of first pixels and the second pixel, wherein
the control unit causes the plurality of first pixels to accumulate
electric charge corresponding to a radiation dose, while causing
the second pixel to operate in a detection cycle determined based
on irradiation information of radiation before irradiation with
radiation, obtains a dose of incident radiation for each detection
cycle, and corrects the obtained radiation dose in accordance with
an amount of noise output from the second pixel operating in the
detection cycle.
[0008] According to some other embodiments, a radiation imaging
system comprising: a radiation imaging apparatus; and a signal
processing unit configured to process a signal from the radiation
imaging apparatus, wherein the radiation imaging apparatus
comprises: a plurality of first pixels arranged in an image sensing
region to obtain a radiation image; a second pixel configured to
obtain a dose of incident radiation during irradiation with
radiation; and a control unit configured to control the plurality
of first pixels and the second pixel, wherein the control unit
causes the plurality of first pixels to accumulate electric charge
corresponding to a radiation dose, while causing the second pixel
to operate in a detection cycle determined based on irradiation
information of radiation before irradiation with radiation, obtains
a dose of incident radiation for each detection cycle, corrects the
obtained radiation dose in accordance with an amount of noise
output from the second pixel operating in the detection cycle,
stops irradiation with radiation based on a radiation dose after
correction, and reads out electric charge accumulated in the
plurality of first pixels after irradiation with radiation.
[0009] According to some other embodiments, a method of controlling
a radiation imaging apparatus including a plurality of first pixels
arranged in an image sensing region to obtain a radiation image,
and a second pixel configured to obtain a dose of incident
radiation during irradiation with radiation, the method comprising:
causing the plurality of first pixels to accumulate electric charge
corresponding to a radiation dose; while causing the second pixel
to operate in a detection cycle determined based on irradiation
information of radiation before irradiation with radiation,
obtaining a dose of incident radiation for each detection cycle;
and correcting the obtained radiation dose in accordance with an
amount of noise output from the second pixel operating in the
detection cycle.
[0010] According to some other embodiments, a program stored in a
non-transitory storage medium for causing a computer to execute a
method of controlling a radiation imaging apparatus including a
plurality of first pixels arranged in an image sensing region to
obtain a radiation image, and a second pixel configured to obtain a
dose of incident radiation during irradiation with radiation, the
method comprising: causing the plurality of first pixels to
accumulate electric charge corresponding to a radiation dose; while
causing the second pixel to operate in a detection cycle determined
based on irradiation information of radiation before irradiation
with radiation, obtaining a dose of incident radiation for each
detection cycle; and correcting the obtained radiation dose in
accordance with an amount of noise output from the second pixel
operating in the detection cycle.
[0011] Further features of the present invention will become
apparent from the following description of exemplary embodiments
(with reference to the attached drawings).
BRIEF DESCRIPTION OF THE DRAWINGS
[0012] FIGS. 1A and 1B are block diagrams showing the arrangement
of a system using a radiation imaging apparatus according to the
present invention;
[0013] FIG. 2 is a circuit diagram of the radiation imaging
apparatus in FIGS. 1A and 1B;
[0014] FIGS. 3A to 3C are plan views and a sectional view of pixels
of the radiation imaging apparatus in FIGS. 1A and 1B;
[0015] FIGS. 4A and 4B are flowcharts of processing performed by
the system using the radiation imaging apparatus in FIGS. 1A and
1B;
[0016] FIGS. 5A and 5B are timing charts in the system using the
radiation imaging apparatus in FIGS. 1A and 1B;
[0017] FIG. 6 is a timing chart showing a modification of each of
the timing charts of FIGS. 5A and 5B;
[0018] FIGS. 7A and 7B are flowcharts showing modifications of the
flowcharts of FIGS. 4A and 4B; and
[0019] FIG. 8 is a view for explaining an example of the
arrangement of a radiation imaging system using the radiation
imaging apparatus according to the present invention.
DESCRIPTION OF THE EMBODIMENTS
[0020] A detailed embodiment of a radiation imaging apparatus
according to the present invention will now be described with
reference to the accompanying drawings. Note that in the following
description and drawings, common reference numerals denote common
components throughout a plurality of drawings. Hence, the common
components will be described by cross-referring to the plurality of
drawings, and a description of components denoted by common
reference numerals will appropriately be omitted. Note that
radiation according to the present invention can include not only
.alpha.-rays, .beta.-rays, and .gamma.-rays that are beams
generated by particles (including photons) emitted by radioactive
decay but also beams having energy equal to or higher than the
energy of these beams, for example, X-rays, particle beams, and
cosmic rays.
[0021] A radiation imaging apparatus according to some embodiments
of the present invention will be described with reference to FIGS.
1A to 6. FIG. 1A shows an example of the arrangement of a radiation
imaging apparatus 200 according to a first embodiment of the
present invention. The radiation imaging apparatus 200 includes a
detecting unit 223, a signal processing unit 224, a control unit
225, and a power supply circuit 226. The control unit 225 supplies
control signals to the detecting unit 223, the signal processing
unit 224, and the power supply circuit 226 to control the
respective constituent elements of the radiation imaging apparatus
200. The detecting unit 223 includes a support substrate 100, a
pixel array 228, a driving circuit 221, and a readout circuit 222.
The pixel array 228 is arranged on the support substrate 100. The
pixel array 228 is arranged in an image sensing region on the
support substrate 100 and includes a plurality of first pixels
including a plurality of conversion elements for obtaining a
radiation image and a second pixel including a detecting element
for obtaining a total incident radiation dose during irradiation
with radiation. The driving circuit 221 drives the pixel array 228.
The readout circuit 222 reads out, as an electrical signal, a
signal generated from radiation incident on each conversion element
and each detecting element of the pixel array 228. The signal
processing unit 224 transfers the electrical signal from the
detecting element, which is read out from the readout circuit 222,
to the control unit 225. The control unit 225 outputs a signal for
controlling the radiation sampling operation of the detecting unit
223 or irradiation with radiation from a radiation source 227 in
accordance with this electrical signal from the detecting element.
The signal processing unit 224 also supplies the electrical signal
read out from the readout circuit 222 to an image processing unit
(not shown) provided outside the radiation imaging apparatus 200 in
accordance with a control signal supplied from the control unit
225. Upon receiving the electrical signal, the image processing
unit (not shown) may generate an image from the electrical signal
and output it to a display (not shown). This allows the user of the
radiation imaging apparatus 200 to observe a radiation image
obtained by image sensing. In addition, the signal processing unit
224 may perform imaging processing of an electrical signal. The
power supply circuit 226 applies a bias voltage to each constituent
element of the radiation imaging apparatus 200. In this embodiment,
the signal processing unit 224 and the control unit 225 are
separate components. However, for example, the control unit 225 may
have an integrated arrangement to perform the processing of the
signal processing unit 224.
[0022] The radiation source 227 and a radiation control unit 229
are connected to the radiation imaging apparatus 200. The radiation
source 227 performs irradiation with radiation. The radiation
control unit 229 controls the radiation source 227. The radiation
control unit 229 controls the radiation source 227 in accordance
with a control signal supplied from the control unit 225. In this
embodiment, the radiation control unit 229 controls the radiation
source 227. However, the control unit 225 may directly supply a
control signal to the radiation source 227 without going through
the radiation control unit 229. In addition, for example, although
the radiation imaging apparatus 200 and the radiation control unit
229 are separately arranged in the embodiment, the radiation
imaging apparatus 200 may include at least part of the function of
the radiation control unit 229. In addition, the radiation imaging
apparatus 200 and the radiation control unit 229 may be integrally
arranged.
[0023] When performing radiation imaging, it is possible to
externally input imaging conditions such as a tube current and a
tube voltage to the radiation control unit 229. In addition,
conditions such as a radiation irradiation time can be externally
input to the radiation control unit 229 and used for control of the
radiation source 227. The user may directly input values
representing imaging conditions such as a tube current, a tube
voltage, and an irradiation time to the radiation control unit 229.
In addition, imaging conditions may be set in advance for each
imaging mode, and the user may select conditions from imaging
condition recipes saved in, for example, the radiation control unit
229. The radiation control unit 229 may have a user interface which
receives inputs of information such as imaging conditions from the
user and use a personal computer as a constituent element. The
radiation control unit 229 may also include a control console
attached to a radiation generator including a radiation source.
[0024] The detecting unit 223 will be described next with reference
to FIG. 2. The detecting unit 223 includes the support substrate
100 on which the pixel array 228 is arranged as described above,
the driving circuit 221, and the readout circuit 222. The pixel
array 228 includes a plurality of pixels arranged in matrix. The
plurality of pixels includes first pixels 101 and a second pixel
121.
[0025] In order to obtain a radiation image, each first pixel 101
includes a conversion element 102 which converts incident radiation
or light into electric charge corresponding to the amount of
incident radiation or light and a switch element 103 which outputs
electric charge generated by the conversion element 102 to a signal
line. The conversion element 102 may be an indirect type conversion
element using a scintillator which converts, for example, radiation
into light and a photoelectric conversion element which converts
the light obtained by the scintillator into electric charge.
Alternatively, as the conversion element 102, a direct type
conversion element may be used, which directly converts, for
example, radiation into electric charge. As the switch element 103,
a TFT (Thin-Film Transistor) using, for example, amorphous silicon
or poly silicon may be used. For example, poly silicon may be used
in accordance with characteristics required for a TFT. In addition,
a semiconductor material used for a TFT is not limited to silicon,
and other semiconductor materials such as germanium and compound
semiconductors may be used.
[0026] A first main electrode of the switch element 103 is
electrically connected to a first electrode of the conversion
element 102. A bias line 108 is electrically connected to a second
electrode of the conversion element 102. The bias line 108 is
commonly connected to the second electrodes of a plurality of
conversion elements 102 arranged along a column. A common bias
voltage is applied to the bias lines 108 provided for the
respective columns. Each bias line 108 receives a bias voltage from
the power supply circuit 226 shown in FIG. 1.
[0027] A signal line 106 is electrically connected to a second main
electrode of each switch element 103. The second main electrodes of
the switch elements 103 arranged along each column are commonly
connected to the signal line 106. The signal line 106 is provided
for each pixel column. Each signal line 106 is electrically
connected to the readout circuit 222. A driving line 104 is
electrically connected to the control electrode of each switch
element 103. The driving line 104 is commonly connected to the
control electrodes of the switch elements 103 of the plurality of
first pixels 101 arranged along each row. Gate control voltages Vg1
to Vgn are applied from the driving circuit 221 to the respective
driving lines 104.
[0028] Each second pixel 121 includes a detecting element 122 which
converts incident radiation or light into electric charge
corresponding to the incident amount to obtain a total incident
radiation dose during irradiation with radiation and a switch
element 123 which outputs the electric charge generated by the
detecting element 122 to a signal line. In addition, each second
pixel 121 may include the conversion element 102 and the switch
element 103. The detecting element 122 and the switch element 123
may respectively have the same arrangements as those of the
conversion element 102 and the switch element 103.
[0029] The first main electrode of the switch element 123 is
electrically connected to the first electrode of the detecting
element 122, and the bias line 108 provided for each column is
electrically connected to the second electrode of the detecting
element 122. The second main electrodes of the switch elements 123
arranged along each column are connected to a detection line 110.
Each detection line 110 is electrically connected to the readout
circuit 222. A driving line 124 provided for each row is connected
to the control electrode of the switch element 123. Gate control
voltages Vd1 to Vdn are applied from the driving circuit 221 to the
respective driving lines 124.
[0030] A plurality of second pixels 121 may be arranged in an image
sensing region, as shown in FIG. 2, or only one second pixel 121
may be arranged in the region. If a plurality of second pixel 121
is arranged, an incident radiation dose may be detected by only one
of the detecting elements 122 of the plurality of second pixels 121
or a plurality of detecting elements.
[0031] In the readout circuit 222, the signal lines 106 and
detection lines 110 are respectively connected to the inverting
input terminals of operational amplifiers 150. The inverting input
terminal of each operational amplifier 150 is connected to an
output terminal via a feedback capacitor. The non-inverting input
terminal of each operational amplifier 150 is connected to an
arbitrary fixed potential. Each operational amplifier 150 functions
as an electric charge/voltage conversion circuit. An A/D converter
153 is connected to the output stage of each operational amplifier
150 via a sample/hold circuit 151 and a multiplexer 152. The
readout circuit 222 forms a digital conversion circuit which
converts electric charge transferred from the conversion elements
102 and the detecting elements 122 of the first pixels 101 and the
second pixels 121 via the signal lines 106 and detection lines 110
into electrical signals as digital signals. The readout circuit 222
may be individually arranged for each circuit upon integration of
each circuit.
[0032] The structures of the first and second pixels 101 and 121
according to this embodiment will be described next with reference
to FIGS. 3A to 3C. FIG. 3A is a plan view of the first pixel 101.
FIG. 3B is a plan view of the second pixel 121. FIG. 3C is a
sectional view showing the second pixel 121 taken along a line A-A'
in FIG. 3B. This embodiment uses an indirect type conversion
element using a scintillator which converts radiation into light
and a photoelectric conversion element which converts light
obtained by the scintillator into electric charge. As shown in FIG.
3A, the conversion element 102 and the switch element 103 are
arranged in the first pixel 101. In addition, as shown in FIG. 3B,
the conversion element 102, the switch element 103, the detecting
element 122, and the switch element 123 are arranged in the second
pixel 121. As shown in FIG. 3C, the conversion element 102 may use
a PIN photodiode 134. Like the conversion element 102, the
detecting element 122 may also use a PIN photodiode 135. The
conversion element 102 is stacked on a dielectric interlayer 130 on
the switch element 103 using the TFT provided on the insulating
support substrate 100 such as a glass substrate. Likewise, the
detecting element 122 is stacked on the dielectric interlayer 130
on the switch element 123 using the TFT provided on the support
substrate 100.
[0033] The conversion element 102 and the detecting element 122 are
insulated so as not to electrically conduct to first and second
electrodes 131 and 132 of the conversion element 102 and the
detecting element 122 which are respectively adjacent to the
conversion element 102 and the detecting element 122, and an
inter-element insulating film 133 improves the insulation between
the first electrodes 131 and 132. The PIN photodiodes 134 and 135
are stacked on the first electrodes 131 and 132 and the
inter-element insulating film 133 in the order of n-layer, i-layer,
and p-layer. Second electrodes 136 and 137 are respectively
arranged on the photodiodes 134 and 135. A protective film 138, a
second dielectric interlayer 139, the bias line 108, and a
protective film 140 are arranged so as to cover the photodiodes 134
and 135. A planarization film (not shown) and a scintillator (not
shown) are arranged on the protective film 140. The second
electrodes 136 and 137 are both connected to the bias line 108. In
this embodiment, for example, light-transmitting electrodes such as
indium tin oxide (ITO) electrodes are used for the second
electrodes 136 and 137. The second electrodes 136 and 137 are
configured to transmit light converted from radiation by a
scintillator (not shown) on the protective film 140 to the
photodiodes 134 and 135.
[0034] As shown in FIGS. 3A and 3B, the first pixel 101 differs in
the size of the conversion element 102 from the second pixel 121.
For this reason, even if the amount of radiation incident on the
first pixel 101 is the same as that on the second pixel 121, the
respective conversion elements 102 output different amounts of
electric charge. When using, for a radiation image, an electrical
signal read out from electric charge output from the conversion
element 102 of the second pixel 121 by using the readout circuit
222, it is preferable to perform necessary correction such as white
balance correction (gain correction). Alternatively, for example,
only the detecting element 122 may be arranged in the second pixel
121, with no conversion element 102 being arranged. In this case,
although some pixels output no electrical signal for the formation
of a radiation image, a radiation image may be corrected by using
electrical signals output from the first pixels 101 arranged around
the second pixel 121. In addition, in the detecting element 122, an
electrical signal used for the detection of an incident radiation
dose may be used for the formation of a radiation image.
[0035] An operation procedure of each constituent element of the
radiation imaging apparatus will be described next with reference
to FIG. 4A. FIG. 4A is a flowchart when performing image sensing in
this embodiment. First of all, the user inputs image sensing
information on the user interface of the radiation control unit
229. The image sensing information includes, for example, the tube
voltage and tube current of the radiation source, an irradiation
time, and a target radiation dose. In addition, if the pixel array
228 is provided with a plurality of detecting elements 122, the
image sensing information may include the information of the
position of the detecting element 122, of the plurality of
detecting elements 122, which obtains an incident radiation dose,
that is, a position at which an incident radiation dose is
obtained. In addition, when forming one pixel of a radiation image
by using outputs from a plurality of first pixels 101 or an output
from the conversion element 102 of the second pixel 121, the image
sensing information may include a binning count and a gain setting
in the readout circuit 222. In addition, the user may select a
combination of image sensing information set in advance from
recipes saved in the radiation control unit 229 instead of
inputting image sensing information piece by piece. Alternatively,
the radiation control unit 229 may automatically determine a
combination of image sensing information when, for example, the
user inputs an image sensing region or the age, physical size, and
the like of an object. The radiation control unit 229 supplies
radiation irradiation information such as an irradiation time and a
target radiation dose of the image sensing information to the
control unit 225 of the radiation imaging apparatus 200.
[0036] In this embodiment, the control unit 225 determines a
detection cycle of detecting the dose of radiation incident on the
detecting element 122 during a radiation irradiation period during
which a radiation image is obtained, based on irradiation time
information of the radiation irradiation information input from the
radiation control unit 229. The control unit 225 may determine a
detection cycle so as to make a sampling count constant with
respect to, for example, an irradiation time. In this case, a
detection cycle may be determined by calculation using, for
example, a calculation unit such as an FPGA mounted in the control
unit 225. Alternatively, for example, the relationship between
irradiation times and detection cycles may be stored as an LUT
(LookUp Table) in the memory of the control unit 225 in advance,
and a detection cycle may be determined from the information of the
LUT in consideration of an irradiation time input from the
radiation control unit 229.
[0037] For example, the control unit 225 divides an irradiation
time input from the radiation control unit 229 so as to set the
sampling count to 100, and uses each divided time as a detection
cycle. In this case, if the irradiation time is 300 ms, the
detection cycle is determined as 3 ms. If the irradiation time is
100 ms, the detection cycle is determined as 1 ms.
[0038] In addition, when forming one pixel of a radiation image by
using outputs from the plurality of conversion elements 102
included in the plurality of first pixels 101 or the second pixels
121 included in the radiation imaging apparatus 200, the control
unit 225 may determine a detection cycle based on a binning count.
If, for example, the binning count is large with respect to one
piece of irradiation time information, it is possible to increase
the sampling count and shorten the detection cycle. If the binning
count is small, it is possible to decrease the sampling count and
prolong the detection cycle.
[0039] Upon determining a detection cycle, the control unit 225
determines the amount of noise output from the second pixel 121
which operates in the determined detection cycle, based on the
determined detection cycle, before irradiation with radiation. For
example, the control unit 225 may cause the second pixel 121 to
perform the same operation as that at the time of irradiation with
radiation before irradiation with radiation in the determined
detection cycle, and use the signal value of an electrical signal
output from the second pixel 121 as an amount of noise. It is
possible to use, as an amount of noise, a signal value obtained by
causing the second pixel 121 to operate once in the determined
detection cycle or signal values obtained by causing the second
pixel 121 to operate a plurality of times. If a plurality of signal
values is obtained by causing the second pixel 121 to operate a
plurality of times, for example, the average value of the
respective signal values may be used as an amount of noise.
Obtaining a plurality of signal values and averaging them can
suppress the influence of random components of noise output from
the second pixel 121. The amount of noise is used to correct the
radiation dose obtained by the second pixel 121 during irradiation
with radiation.
[0040] When the user turns on an exposure switch provided for the
radiation control unit 229 after the determination of a detection
cycle and an amount of noise, the radiation control unit 229
outputs an exposure instruction to the radiation source 227 and the
control unit 225 of the radiation imaging apparatus 200. The
radiation source 227 starts irradiation with radiation in
accordance with the exposure instruction. In addition, the control
unit 225 causes the detecting unit 223 to operate in accordance
with the exposure instruction and starts obtaining a radiation
image. More specifically, the control unit 225 accumulates electric
charge corresponding to the dose of radiation incident on each of
the conversion elements 102 of the first pixels 101 arranged in the
pixel array 228 of the detecting unit 223. At the same time, the
control unit 225 causes the detecting element 122 of the second
pixel 121 to start a detecting operation of obtaining an incident
radiation dose in the detection cycle determined in advance. In
this case, the exposure switch may be a two-stage switch including
a switch for starting idling the radiation tube of the radiation
source 227 and a switch for irradiating an object with radiation.
In this case, when the switch for starting idling the radiation
tube is turned on, the control unit 225 may cause a detecting
element to operate in the detection cycle determined in advance
from radiation irradiation information and determine an amount of
noise. Upon determining the amount of noise based on the detection
cycle, the control unit 225 starts obtaining a radiation image by
irradiating the object with radiation.
[0041] The control unit 225 then corrects the radiation dose
obtained by the detecting element 122 of the second pixel 121 for
each detection cycle in accordance with the noise amount determined
before irradiation with radiation, and obtains the cumulative total
value of radiation doses after correction. The control unit 225
then compares the cumulative total value of radiation doses with
the target radiation dose information of irradiation information
supplied from the radiation control unit 229. The control unit 225
performs exposure stop determination of determining whether to
continue or stop irradiation with radiation, based on the result
obtained by comparing the cumulative total value of the radiation
doses after correction with the target radiation dose. If the
cumulative total value of the radiation doses detected by the
detecting element 122 of the second pixel 121 has not reached the
target radiation dose, the control unit 225 determines that it is
necessary to continue irradiation with radiation, and continues to
obtain a radiation image and perform a detecting operation. If the
cumulative total value of the radiation doses detected by the
detecting element 122 of the second pixel 121 has reached the
target radiation dose of radiation to be applied or is expected to
reach the target radiation dose, a stop determination signal for
stopping irradiation with radiation is output to the radiation
control unit 229. The radiation control unit 229 outputs an
exposure stop instruction to the radiation source 227 based on the
stop determination signal output from the control unit 225. The
radiation source 227 stops irradiation with radiation in accordance
with the exposure stop instruction. When stopping irradiation with
radiation, the control unit 225 may stop irradiation with radiation
by inhibiting the radiation control unit 229 from outputting an
exposure instruction to the radiation source 227 instead of
outputting an exposure stop instruction. In addition, the detecting
unit 223 may stop a detecting operation in accordance with the
exposure stop instruction.
[0042] In this embodiment, the control unit 225 of the radiation
imaging apparatus 200 performs exposure stop determination.
However, this is not exhaustive. For example, as shown in FIG. 4B,
the control unit 225 outputs, to the radiation control unit 229,
the cumulative total value of radiation doses obtained by
correcting the radiation dose detected by the detecting element 122
of the second pixel 121 in accordance with an amount of noise. The
radiation control unit 229 may perform stop determination based on
this corrected cumulative total value of radiation doses and output
an exposure stop instruction. In this case, before irradiation with
radiation, the radiation control unit 229 supplies irradiation time
information of image sensing information as irradiation information
to the control unit 225 but need not send target radiation dose
information to the control unit 225. In addition, the control unit
225 may stop obtaining a radiation image and detecting a radiation
dose in accordance with an exposure stop instruction output from
the radiation control unit 229 upon its exposure stop
determination.
[0043] In addition, the control unit 225 may output an exposure
stop signal when the irradiation time of irradiation of an object
with radiation from the radiation source 227 reaches the upper
limit of irradiation times of irradiation time information supplied
from the radiation control unit 229 before the irradiation with
radiation. In accordance with the exposure stop signal, the
radiation control unit 229 outputs an exposure stop instruction to
the radiation source 227, and the radiation source 227 stops
irradiation with radiation. Even before the cumulative total value
of the doses of radiation incident on the detecting element 122
reaches a target radiation dose or is expected to reach the target
radiation dose, irradiation with radiation is stopped in accordance
with the upper limit of irradiation times. Even if the dose of
radiation incident on the detecting element 122 of the second pixel
121 is not normally detected, excessive irradiation of an object
with radiation can be avoided.
[0044] The operation timing of each constituent element of the
radiation imaging apparatus according to this embodiment will be
described next with reference to FIGS. 2, 4A, 4B, 5A, and 5B. FIGS.
5A and 5B are timing charts each showing the operation timing of
each constituent element of the radiation imaging apparatus 200. A
period T1 shown in FIGS. 4A, 4B, 5A, and 5B indicates an idling
period during standby. In the period T1, as shown in FIGS. 5A and
5B, the pixel array 228 repeats an idling operation in accordance
with a signal applied from the driving circuit 221. The idling
operation may be performed, for example, until the start of image
sensing after the power supply of the detecting unit 223 is turned
on. Referring to FIGS. 4A and 4B, the period T1 is a time during
which the user inputs image sensing information, a time before the
user presses the exposure switch, or a time during which the
control unit 225 of the radiation imaging apparatus 200 determines
a detection cycle.
[0045] In the period T1, in order to periodically remove dark
currents generated from the conversion elements 102, Hi signals are
periodically applied to the gate control voltages Vg1 to Vgn to
scan the switch elements 103 of the first pixels 101. Likewise, in
order to remove dark currents generated from the detecting elements
122 of the second pixels 121, Hi signals are always applied to the
gate control voltages Vd1 to Vdn to set the switch elements 123 of
the second pixels 121 in a conducting state. In this case, a Hi
signal is a voltage at which each of the switch elements 103 and
123 is turned on. A Lo signal is a voltage (for example, 0 V) at
which each of the switch elements 103 and 123 is turned off. The
timing charts according to this embodiment shown in FIGS. 5A and 5B
each show an example of detecting an incident radiation dose by
using a plurality of detecting elements 122. In this case, the same
target radiation dose or different target radiation doses may be
set in the respective detecting elements 122. In addition, the
control unit 225 may output a stop determination signal when one of
the detecting elements 122 of the plurality of second pixels 121
reaches the target radiation dose or when all the detecting
elements 122 reach the target radiation dose or doses. These
settings may be made as needed in accordance with an object, image
sensing conditions, the positions of the detecting elements 122 in
the pixel array 228, and the like.
[0046] When the user presses the exposure switch or the switch for
starting idling of the radiation tube of the radiation source 227,
a transition occurs to a period T2. The period T2 is a time during
which the amount of noise from each second pixel 121 is determined,
and a radiation image is then obtained by irradiation with
radiation. FIGS. 5A and 5B show timing charts each showing a case
in which image sensing is started when the user turns on the
exposure switch. In the period T2, Lo signals are applied to the
gate control voltages Vg1 to Vgn for driving the switch elements
103, and each conversion element 102 accumulates electric charge
corresponding to an incident radiation dose. In addition, Hi
signals are applied to the gate control voltages Vd1 to Vdn for
driving the switch elements 123 in a detection cycle determined in
the period T1, and electric charge detected by each detecting
element 122 is sent to the readout circuit 222 via the detection
line 110. The readout circuit 222 supplies an electrical signal
based on the detected electric charge to the control unit 225 via
the signal processing unit 224. The control unit 225 obtains the
dose of radiation incident on each detecting element 122 in the
detection cycle.
[0047] First of all, the control unit 225 obtains an amount of
noise from each second pixel 121 in accordance with an electrical
signal read out to the readout circuit 222 before the user presses
the exposure switch to perform irradiation with radiation. FIGS. 5A
and 5B are timing charts in cases in which irradiation times of
irradiation information transferred from the radiation control unit
229 to the control unit 225 in advance differ from each other. FIG.
5B shows a case in which an irradiation time shorter than that in
the case shown in FIG. 5A is input, and hence the gate control
voltages Vd1 to Vdn become Hi signals in shorter cycles. Referring
to the timing chart shown in FIG. 5A, a signal value output once
from the second pixel 121 is used as an amount of noise. Referring
to the timing chart shown in FIG. 5B, since the detection cycle is
short, an average value of two signal values output from the second
pixel 121 before irradiation with radiation is used as an amount of
noise. Averaging a plurality of obtained signal values can obtain
noise while suppressing the influence of random noise even when a
signal amount is small because of a short detection cycle. This
makes it possible to more accurately perform correction when
obtaining the cumulative total value of the doses of radiation
incident during irradiation with radiation. After the noise amount
of each detecting element 122 is determined, irradiation of
radiation is performed. Each conversion element 102 then
accumulates electric charge corresponding to an incident radiation
dose, thereby obtaining a radiation image.
[0048] Referring to FIGS. 5A and 5B, the gate control voltages Vd1
to Vdn applied to the control electrodes of the switch elements 123
simultaneously become Hi signals. However, the operation in the
period T2 is not limited to this. For example, as shown in FIG. 6,
the gate control voltages Vd1 to Vdn corresponding to the switch
elements 123 of the detecting elements 122 connected to the same
detection line 110 may become Hi signals at different timings. In
this case, although the amount of signals that can be read out once
decreases, the spatial resolution of a detection region can be
increased.
[0049] The operational amplifiers 150 convert electric charge sent
from the detecting elements 122 to the readout circuit 222 into
voltage information. The sample/hold circuits 151 then sample the
voltage information based on a detection cycle. The A/D converter
153 converts the sampled information into an electrical signal via
the multiplexers 152.
[0050] The control unit 225 corrects a radiation dose obtained by
converting electric charge detected by each detecting element 122
into an electrical signal in accordance with an amount of noise.
Thereafter, the control unit 225 performs exposure stop
determination based on the cumulative total value of corrected
radiation doses and target radiation dose information transferred
from the radiation control unit 229 to the control unit 225. When
the cumulative total value of radiation doses reaches the target
radiation dose or is expected to reach the target radiation dose,
the control unit 225 outputs a stop determination signal for
stopping irradiation with radiation to the radiation control unit
229. The radiation control unit 229 then causes the radiation
source 227 to stop irradiation with radiation. The duration of the
period T2 may be determined for each image sensing mode or an
irradiation time input in advance. Even if the radiation dose does
not reach the target radiation dose as in the above case, when the
irradiation time reaches the upper limit of irradiation times input
as irradiation information, the control unit 225 stops irradiation
with radiation. After the cumulative total value of radiation doses
detected by the detecting elements 122 reaches the target radiation
dose or a predetermined time elapses, a transition occurs from the
period T2 to a period T3.
[0051] The period T3 is a period during which after irradiation
with radiation, radiation images are obtained by image sensing. In
the period T3, the control unit 225 outputs control signals to the
driving circuit 221 to read out signal charge accumulated in the
conversion elements 102. The driving circuit 221 sequentially
applies Hi signals to the gate control voltages Vg1 to Vgn in
accordance with the control signals to sequentially scan the switch
elements 103 of the first and second pixels 101 and 121. The
operational amplifiers 150 convert electric charge accumulated in
the conversion elements 102 into voltage information. The
sample/hold circuits 151 then sample the voltage information. The
A/D converter 153 converts the sampled information into an
electrical signal as digital data via the multiplexers 152. A
radiation image is formed based on electrical signals obtained by
the conversion elements 102 and read out.
[0052] The effects of this embodiment will be described below. In
the period T2 shown in each of FIGS. 5A and 5B, a detection signal
is sampled from each second pixel 121 in a proper detection cycle
based on an irradiation time input in advance. Therefore, when the
radiation irradiation time is long and low-energy radiation is
incident at a low dose per unit time, setting a long detection
cycle will prolong the accumulation time of signals and suppress
the possibility that detection signals will be buried in noise.
When the radiation irradiation time is short and high-energy
radiation is incident at a high dose per unit time, setting a short
detection cycle makes it possible to obtain detection signals
without saturating the capacity of each detecting element 122 in
terms of accumulating electric charge.
[0053] In addition, the amount of noise output from each second
pixel 121 can change depending on operation conditions for the
detecting element 122 and the switch element 123. For example, a
dark current in the detecting element 122 or the offset level of
the switch element 123 may change depending on a detection cycle or
a temperature at the time of image sensing. The influences of such
changes can change the amount of noise output from each second
pixel 121. In this embodiment, therefore, before irradiation with
radiation, the amount of noise output from each second pixel is
obtained in the same detection cycle as when detecting radiation.
This makes it possible to obtain an amount of noise in accordance
with a detection cycle or image sensing environment for each second
pixel 121.
[0054] Each second pixel 121 is operated in a proper detection
cycle based on radiation irradiation information of image sensing
information input in advance by the user. In addition, the noise
amount of the second pixel 121 is obtained in the same detection
cycle. Thereafter, irradiation with radiation is performed, and a
radiation dose obtained by the second pixel 121 during irradiation
with radiation is corrected in accordance with the amount of noise
to obtain the dose of radiation actually incident on the radiation
imaging apparatus 200. This can set an exposure amount at the time
of image sensing to a more proper exposure amount at the time of
image sensing and hence can improve the quality of a sensed
image.
[0055] A radiation imaging apparatus according to a second
embodiment of the present invention will be described with
reference to FIG. 7A. FIG. 7A is a flowchart for explaining the
operation of each constituent element of the radiation imaging
apparatus according to this embodiment at the time of image
sensing. A radiation imaging apparatus 200, a radiation control
unit 229, and a radiation source 227 may have the same arrangements
as those shown in FIGS. 1A and 1B in the first embodiment described
above. In the first embodiment, a detection cycle for the detection
of a radiation dose is determined by using, as radiation
irradiation information, irradiation time information of image
sensing information. In contrast to this, the second embodiment
uses, as irradiation information, at least one of the following
pieces of information: the tube voltage and tube current of a
radiation source, the distance between the radiation source and an
object, a grid exposure factor, an object thickness, the radiation
transmittance of an object region of interest, and the radiation
absorptance of an added filter such as an Al filter. A proper
detection cycle is determined by estimating an estimated radiation
dose of radiation incident per unit time concerning the irradiation
dose of radiation or a physical amount correlated with the dose of
incident radiation by using these pieces of information.
[0056] It is possible to input the following pieces of image
sensing information from the radiation control unit 229 as a user
interface: the tube voltage and tube current of the radiation
source, the distance between the radiation source and an object, a
grid exposure factor, an object thickness, the radiation
transmittance of an object region of interest, and the radiation
absorptance of an added filter. Alternatively, sensors may be
provided for the radiation imaging apparatus 200, the radiation
control unit 229, and the radiation source 227 to automatically
obtain some of these pieces of image sensing information. For
example, the distance between the radiation source 227 and an
object may be measured by an infrared sensor attached to the
radiation source 227. In addition, a camera connected to the
radiation control unit 229 may be used to estimate an object
thickness or specify a region of an object as a region of interest
and estimate the radiation transmittance of the object region of
interest. Furthermore, calibration may be performed in advance to
obtain the distance between the radiation source and an object, a
grid exposure factor, the radiation absorptance of the added
filter, and the like. Alternatively, the radiation imaging
apparatus 200 may have a user interface, and the user may input
image sensing information to the interface.
[0057] In this embodiment, the radiation control unit 229 sends, to
the radiation imaging apparatus 200, irradiation information, of
image sensing information, which is associated with the irradiation
dose of radiation with which the radiation imaging apparatus 200 is
irradiated. A control unit 225 of the radiation imaging apparatus
200 calculates an estimated radiation dose of radiation incident
per unit time by using equation (1) given below with respect to
this irradiation information:
E ( t ) = V n I SID 2 1 B Al ( V ) exp - .mu. d ( 1 )
##EQU00001##
where V is a tube voltage, n is a tube voltage index, I is a tube
current, SID is an object distance, B is a grid exposure factor, d
is an object thickness, .mu. is the radiation transmittance of an
object region of interest, A1 (V) is the radiation absorptance of
the added filter, and E(t) is an estimated radiation dose of
radiation incident per unit time. Since the estimated value E(t) of
the dose of radiation incident per unit time is proportional to the
amount of detection signals per unit time, a detection cycle is
determined in proportion to this value.
[0058] If not all the pieces of irradiation information indicated
by equation (1) can be obtained, for example, standard values may
be input concerning parameters whose information has not been
obtained. Inputting at least one of the pieces of irradiation
information makes it possible to bring a detection cycle close to
an optimal value and more accurately obtain the dose of incident
radiation.
[0059] The amount of noise output from each detecting element 122
may be obtained by operating a second pixel 121 in a period T2
before irradiation with radiation as in the first embodiment
described above. Alternatively, each second pixel 121 is operated
in a plurality of detection cycles without irradiation with
radiation in advance, and each signal value output from the second
pixel 121 is stored in a noise amount memory unit 231 provided for
the control unit 225 as shown in FIG. 1A. For example, the control
unit 225 may determine an amount of noise by performing calculation
in accordance with a determined detection cycle by using these
signal values. For example, the second pixel 121 obtains in advance
an amount of noise a obtained in advance in a detection cycle A and
an amount of noise b obtained in a detection cycle B. In this case,
if a detection cycle is determined as a detection cycle C, an
amount of noise c used for correction may be calculated by using
equation (2) given below:
c = a - b 1 A - 1 B .times. 1 C + Bb - Aa B - A ( 2 )
##EQU00002##
[0060] The respective signal values may be obtained in a plurality
of detection cycles, for example, at the time of turning on the
power of the radiation imaging apparatus 200 or during a period T1.
Alternatively, for example, signal values may be obtained in a
plurality of detection cycles at factory shipment, and may be saved
in the noise amount memory unit 231.
[0061] In addition, for example, the relationship between detection
cycles and noise amounts may be stored in the form of an LUT in the
noise amount memory unit 231 in advance, and the control unit 225
may determine an amount of noise from the information of the LUT
with respect to a determined detection cycle. When determining an
amount of noise by the above calculation or using the information
of the LUT, it is possible to determine an amount of noise in the
period T1, as shown in FIG. 7A.
[0062] In this embodiment, in order to determine a detection cycle,
the dose of radiation incident on the radiation imaging apparatus
200 per unit time is estimated by using information concerning the
dose of incident radiation such as the tube voltage or tube current
of the radiation source. If, therefore, the dose of radiation
incident per unit time is small, a long detection cycle is set.
This prolongs the accumulation time of signals, and hence
suppresses the possibility that detection signals are buried in
noise. In contrast to this, if the dose of radiation incident per
unit time is large, a short detection cycle is set. This makes it
possible to obtain a detection signal of a proper signal amount
with respect to the capacity of the detecting element 122, which
allows the accumulation of electric charge. The amount of noise
output from the detecting element 122 is determined in accordance
with the determined detection cycle. This makes it possible to
obtain the dose of radiation incident on the radiation imaging
apparatus 200 with higher accuracy as in the first embodiment. This
can improve the image quality of a sensed image.
[0063] A radiation imaging apparatus according to a third
embodiment of the present invention will be described with
reference to FIGS. 1B and 7B. FIG. 1B shows an example of the
arrangement of a radiation imaging apparatus 200a according to this
embodiment. Unlike the first embodiment shown in FIG. 1A, a
radiation control unit 229 which controls a radiation source 227
connected to the radiation imaging apparatus 200a is connected to a
database 230. This apparatus may be the same as the radiation
imaging apparatus 200 shown in FIG. 1A in other respects.
[0064] The database 230 saves image sensing information concerning
past image sensing conditions including irradiation time
information. In the first embodiment, a detection cycle for the
detection of a radiation dose is determined by using irradiation
time information of image sensing information. In contrast to this,
in the second embodiment, as indicated by the flowchart of FIG. 7B,
when determining a detection cycle, the radiation control unit 229
compares image sensing information input by the user to the user
interface of the radiation control unit 229 with information saved
in the database 230. For example, the user inputs image sensing
information concerning the tube voltage and tube current of
radiation, an image sensing region, an object thickness, and the
like to the radiation control unit 229. The radiation control unit
229 searches the database 230 for past image sensing conditions
having image sensing information similar to the input image sensing
information, and checks the actual value of the time duration of
irradiation with radiation at the image sensing time obtained by
the search. The radiation control unit 229 then transfers the
actual value of the irradiation time to a control unit 225. The
control unit 225 determines a detection cycle based on this actual
value. In addition, the detection cycle may be stored in the
database 230. Based on the determined detection cycle, the control
unit 225 determines the amount of noise output from each second
pixel 121. It is possible to determine an amount of noise by using
either of the methods according to the first and second
embodiments.
[0065] In this embodiment, the radiation control unit 229 searches
the database 230 for information concerning image sensing
information input by the user. However, this is not exhaustive. For
example, the radiation control unit 229 may transfer radiation
irradiation information of image sensing conditions input by the
user to the control unit 225, and the control unit 225 may search
the database 230 for image sensing conditions.
[0066] A method of determining a detection cycle by using the
database 230 is not limited to the above method. For example, when
performing imaging sensing of the same region of the same patient
for a follow-up check or the like, the user inputs a patient name,
a patient identification (ID), and the like to the radiation
control unit 229 to make the radiation control unit 229 obtain
image sensing information such as radiation irradiation conditions
and an irradiation time at the time of image sensing in the past
from the database 230. Based on this image sensing information, the
radiation control unit 229 transfers, to the control unit 225 of
the radiation imaging apparatus 200, irradiation information
concerning the irradiation time and irradiation dose of radiation
with which the radiation imaging apparatus 200 is irradiated. The
control unit 225 may determine a detection cycle based on this
irradiation information.
[0067] Image sensing information concerning past image sensing
conditions to be saved in the database 230 may be accumulated for
each image sensing operation for an object which has actually
undergone image sensing. Alternatively, for example, the database
230 may save image sensing information artificially generated at
factory shipment or at the time of maintenance.
[0068] This embodiment uses past image sensing information such as
the irradiation time of radiation or the like to determine a
detection cycle. This makes it possible to more accurately obtain
the dose of incident radiation. When performing similar image
sensing operations with respect to an object, a detection cycle is
constant. This makes it possible to manage AEC (Automatic Exposure
Control) under the same conditions when using similar image sensing
conditions. In addition, the amount of noise output from each
detecting element 122 is determined in accordance with a determined
detection cycle. As in the first and second embodiments, this makes
it possible to more accurately obtain the dose of radiation
incident on the radiation imaging apparatus 200 and hence to
improve the quality of a sensed image.
[0069] The third embodiment according to the present invention has
been described above. The above embodiments can be changed and
combined with each other, as needed.
[0070] In addition, if the control unit 225 cannot determine at
least either of a detection cycle and an amount of noise, the
radiation imaging apparatus 200 need not perform irradiation with
radiation. If, for example, an input image sensing condition
greatly differs from an approximate recommended value determined by
an image sensing region, sex, age, and the like of an object, the
control unit 225 need not be able to determine a detection cycle or
noise amount by using a mechanism such as an interlock. If a
detection cycle or noise amount cannot be determined, for example,
the control unit 225 need not permit the radiation control unit 229
or the radiation source 227 to start irradiation with radiation. In
addition, for example, if no actual values of irradiation times are
saved in the database 230 or a radiation irradiation time is too
short to determine a detection cycle, the control unit 225 may not
permit the start of irradiation with radiation.
[0071] A radiation imaging system incorporating the radiation
imaging apparatus 200 according to the present invention will be
exemplarily described below with reference to FIG. 8. X-rays 6060
generated by an X-ray tube 6050 as a radiation source are
transmitted through a chest region 6062 of a patient or object 6061
and enter the radiation imaging apparatus 200 according to the
present invention. The incident X-rays include information about
the inside of the body of the patient or object 6061. In the
radiation imaging apparatus 200, the scintillator emits light as
the X-rays 6060 enter, and electrical information is obtained by
photoelectric conversion of the emitted light using photoelectric
conversion elements. This information is converted into a digital
signal. An image processor 6070 serving as a signal processing unit
performs image processing of the signal. It is possible to observe
the resultant image on a display 6080 serving as a display unit in
a control room. In addition, it is possible to transfer this
information to a remote place via a transmission processing unit
such as a telephone line 6090. The information can be displayed on
a display 6081 as a display unit in another place such as a doctor
room or can be stored in a recording unit such as an optical disk.
This makes it possible for a doctor in a remote place to perform
diagnosis. In addition, this information can be recorded on a
recording medium such as an optical disk. Furthermore, a film
processor 6100 can record the information on a film 6110 as a
recording medium.
[0072] Embodiment(s) of the present invention can also be realized
by a computer of a system or apparatus that reads out and executes
computer executable instructions (e.g., one or more programs)
recorded on a storage medium (which may also be referred to more
fully as a `non-transitory computer-readable storage medium`) to
perform the functions of one or more of the above-described
embodiment(s) and/or that includes one or more circuits (e.g.,
application specific integrated circuit (ASIC)) for performing the
functions of one or more of the above-described embodiment(s), and
by a method performed by the computer of the system or apparatus
by, for example, reading out and executing the computer executable
instructions from the storage medium to perform the functions of
one or more of the above-described embodiment(s) and/or controlling
the one or more circuits to perform the functions of one or more of
the above-described embodiment(s). The computer may comprise one or
more processors (e.g., central processing unit (CPU), micro
processing unit (MPU)) and may include a network of separate
computers or separate processors to read out and execute the
computer executable instructions. The computer executable
instructions may be provided to the computer, for example, from a
network or the storage medium. The storage medium may include, for
example, one or more of a hard disk, a random-access memory (RAM),
a read only memory (ROM), a storage of distributed computing
systems, an optical disk (such as a compact disc (CD), digital
versatile disc (DVD), or Blu-ray Disc (BD.TM., a flash memory
device, a memory card, and the like.
[0073] While the present invention has been described with
reference to exemplary embodiments, it is to be understood that the
invention is not limited to the disclosed exemplary embodiments.
The scope of the following claims is to be accorded the broadest
interpretation so as to encompass all such modifications and
equivalent structures and functions.
[0074] This application claims the benefit of Japanese Patent
Application No. 2015-190335, filed Sep. 28, 2015, which is hereby
incorporated by reference wherein in its entirety.
* * * * *