U.S. patent application number 13/729536 was filed with the patent office on 2013-05-09 for radiographic imaging device, radiographic imaging system, and radiographic imaging method.
This patent application is currently assigned to FUJIFILM CORPORATION. The applicant listed for this patent is FUJIFILM Corporation. Invention is credited to Naoyuki NISHINO, Yasunori OHTA.
Application Number | 20130114793 13/729536 |
Document ID | / |
Family ID | 45529953 |
Filed Date | 2013-05-09 |
United States Patent
Application |
20130114793 |
Kind Code |
A1 |
OHTA; Yasunori ; et
al. |
May 9, 2013 |
RADIOGRAPHIC IMAGING DEVICE, RADIOGRAPHIC IMAGING SYSTEM, AND
RADIOGRAPHIC IMAGING METHOD
Abstract
The radiographic imaging device that configures the disclosed
radiographic imaging system has at least a camera that images a
main cassette body. Said camera is integrally configured to a
radiation source and a control device that controls the main
cassette body or is integrally configured to a main radiation
source body that houses the radiation source.
Inventors: |
OHTA; Yasunori;
(Kanagawa-ken, JP) ; NISHINO; Naoyuki;
(Kanagawa-ken, JP) |
|
Applicant: |
Name |
City |
State |
Country |
Type |
FUJIFILM Corporation; |
Tokyo |
|
JP |
|
|
Assignee: |
FUJIFILM CORPORATION
Tokyo
JP
|
Family ID: |
45529953 |
Appl. No.: |
13/729536 |
Filed: |
December 28, 2012 |
Related U.S. Patent Documents
|
|
|
|
|
|
Application
Number |
Filing Date |
Patent Number |
|
|
PCT/JP2011/066405 |
Jul 20, 2011 |
|
|
|
13729536 |
|
|
|
|
Current U.S.
Class: |
378/63 |
Current CPC
Class: |
A61B 5/0059 20130101;
A61B 6/461 20130101; A61B 6/4405 20130101; A61B 6/563 20130101;
A61B 6/4233 20130101; A61B 6/587 20130101; A61B 6/588 20130101;
A61B 6/48 20130101; A61B 6/542 20130101; A61B 6/4291 20130101; A61B
6/548 20130101; A61B 6/4411 20130101 |
Class at
Publication: |
378/63 |
International
Class: |
A61B 6/00 20060101
A61B006/00 |
Foreign Application Data
Date |
Code |
Application Number |
Jul 26, 2010 |
JP |
2010-167255 |
Jul 26, 2010 |
JP |
2010-167257 |
Claims
1. A radiographic image capturing apparatus comprising: a radiation
source for outputting radiation; a radiation detector for detecting
radiation that has passed through a subject and converting the
detected radiation into a radiographic image upon application of
the radiation to the subject from the radiation source; a cassette
device that is permeable to the radiation and accommodates the
radiation detector therein; a camera for capturing an image of at
least the cassette device; and a camera image communication unit
that transmits an image of the cassette device captured by the
camera to a waiting location communication unit provided in a
waiting location where a doctor or radiological technician having
authority to apply the radiation to the subject waits while being
unable to see the subject directly, wherein the camera is made
integral with a controller for controlling the radiation source and
the cassette device, or is made integral with a radiation source
device accommodating the radiation source therein.
2. The radiographic image capturing apparatus according to claim 1,
wherein, at least at times of usage of the radiographic image
capturing apparatus, the camera and the controller are connected
integrally, or the camera and the radiation source device are
connected integrally.
3. The radiographic image capturing apparatus according to claim 2,
wherein: the camera and the controller being connected integrally
implies that the camera is incorporated in the controller, or the
controller and the camera are connected through a cable, or the
controller and the camera are connected at least only at the times
of usage, whereas during maintenance of the radiographic image
capturing apparatus or during times of non-usage thereof, the
camera is capable of being separated from the controller; and the
camera and the radiation source device being connected integrally
implies that the camera is incorporated in the radiation source
device, or the radiation source device and the camera are connected
through a cable, or the radiation source device and the camera are
connected at least only at the times of usage, whereas during
maintenance of the radiographic image capturing apparatus or during
times of non-usage thereof, the camera is capable of being
separated from the radiation source device.
4. The radiographic image capturing apparatus according to claim 1,
wherein: the camera captures at least an image of an irradiated
field of the radiation corresponding to the radiation detector on
an irradiated surface of the cassette device, which is irradiated
by the radiation; and the camera image communication unit transmits
the image of the irradiated field captured by the camera to the
waiting location communication unit.
5. The radiographic image capturing apparatus according to claim 4,
wherein the camera image communication unit is incorporated in the
controller, the radiation source device, the cassette device, or
the camera.
6. The radiographic image capturing apparatus according to claim 5,
wherein: the radiation source device further includes a radiation
source communication unit capable of communicating with the
exterior; the cassette device further includes a cassette
communication unit capable of communicating with the exterior; and
the controller includes a controller communication unit capable of
communicating with the exterior, wherein among the controller
communication unit, the radiation source communication unit, and
the cassette communication unit, any one of the communication units
functions as the camera image communication unit, whereby the image
of the irradiated field captured by the camera is transmitted to
the waiting location communication unit, or alternatively, the
camera image communication unit incorporated in the camera
transmits the image of the irradiated field to the waiting location
communication unit.
7. The radiographic image capturing apparatus according to claim 6,
wherein: in a case that communications between the controller
communication unit, the radiation source communication unit, and
the cassette communication unit are carried out by wired
communications, cables are connected electrically between the
controller communication unit and the radiation source
communication unit, and between the controller communication unit
and the cassette communication unit.
8. The radiographic image capturing apparatus according to claim 6,
wherein the cassette communication unit transmits the radiographic
image directly to the waiting location communication unit, or
alternatively, transmits the radiographic image to the waiting
location communication unit via at least one of the controller
communication unit, the radiation source communication unit and the
camera image communication unit.
9. The radiographic image capturing apparatus according to claim 6,
wherein transmission and reception of the image of the irradiated
field is carried out by at least one of wireless communications and
wired communications between the camera image communication unit
and the waiting location communication unit, and transmission and
reception of the radiographic image is carried out by at least one
of wireless communications and wired communications between the
cassette communication unit and the waiting location communication
unit.
10. The radiographic image capturing apparatus according to claim
6, wherein: a console, which is connected electrically to the
waiting location communication unit, is further provided at the
waiting location; and the waiting location communication unit
outputs to the console at least one of the received image of the
irradiated field and the radiographic image.
11. The radiographic image capturing apparatus according to claim
10, wherein: an exposure switch, which is capable of initiating
output of the radiation from the radiation source, is provided on
the console; in response to turning on the exposure switch, the
console transmits an exposure control signal for initiating output
of the radiation to the radiation source communication unit via the
waiting location communication unit; and the radiation source
initiates output of the radiation in response to reception of the
exposure control signal by the radiation source communication
unit.
12. The radiographic image capturing apparatus according to claim
11, wherein the controller further includes at least one of a
display unit capable of displaying at least one of the image of the
irradiated field and the radiographic image, and an audio output
unit for outputting speech sounds to the exterior.
13. The radiographic image capturing apparatus according to claim
12, wherein: in a case that the region to be imaged of the subject
is not visible in, or if only a portion of the region to be imaged
is visible within the image of the irradiated field, which is
output to the console prior to output of the radiation from the
radiation source, the console does not output the exposure control
signal to the waiting location communication unit, but instead
transmits an instruction signal to the controller communication
unit via the waiting location communication unit for instructing
the radiographic image capturing apparatus, so that the region to
be imaged of the subject is visible within the image of the
irradiated field; and based on the instruction signal, which is
received by the controller communication unit, the controller
performs at least one of displaying of instruction content
indicative of the instruction signal on the display unit and
outputting of speech sounds corresponding to the instruction
content from the audio output unit to the outside.
14. The radiographic image capturing apparatus according to claim
5, wherein: the controller further includes a controller battery
for driving the controller; the radiation source device further
includes a radiation source battery for driving the radiation
source; the cassette device further includes a cassette battery for
driving the radiation detector; and the controller battery is
capable of charging at least one of the radiation source battery
and the cassette battery.
15. The radiographic image capturing apparatus according to claim
1, wherein a handle is provided on the radiation source device on a
side opposite from a location where the radiation is emitted.
16. The radiographic image capturing apparatus according to claim
15, wherein: a gripping state detection sensor, which outputs a
detection signal indicative of the handle being gripped in a case
that the handle is gripped by the operator of the radiographic
image capturing apparatus, is provided on the handle; and the
radiation source device is activated based on the detection
signal.
17. The radiographic image capturing apparatus according to claim
16, wherein: a recess, which is capable of accommodating the handle
therein, is provided on the radiation source device on a side
opposite from a location where the radiation is emitted; and the
gripping state detection sensor outputs the detection signal in a
case that the handle is gripped by the operator in a condition in
which the handle is pulled out from the recess.
18. The radiographic image capturing apparatus according to claim
1, wherein the camera image communication unit transmits to the
waiting location communication unit a moving image or a still image
of the cassette device captured by the camera, or still images of
the cassette device captured by the camera at predetermined time
intervals.
19. The radiographic image capturing apparatus according to claim
18, wherein the camera is an optical camera.
20. A radiographic image capturing system comprising: a
radiographic image capturing apparatus having a radiation source
for outputting radiation, a radiation detector for detecting
radiation that has passed through a subject and converting the
detected radiation into a radiographic image upon application of
the radiation to the subject from the radiation source, a cassette
device that is permeable to the radiation and accommodates the
radiation detector therein, a camera for capturing an image of at
least the cassette device, and a camera image communication unit
that externally transmits an image of the cassette device captured
by the camera; and a console and a waiting location communication
unit which are disposed at a waiting location where a doctor or
radiological technician having authority to apply the radiation to
the subject waits while being unable to see the subject directly,
the waiting location communication unit being adapted to receive an
image of the cassette device from the camera image communication
unit, the console being connected electrically to the waiting
location communication unit, the image of the cassette device being
input from the waiting location communication unit to the console,
wherein the camera is made integral with a controller of the
radiographic image capturing apparatus for controlling the
radiation source and the cassette device, or is made integral with
a radiation source device accommodating the radiation source
therein.
21. The radiographic image capturing system according to claim 20,
wherein the controller generates a synchronization control signal
for synchronizing emission of the radiation from the radiation
source and conversion of the radiation into a radiographic image in
the radiation detector with each other, and controls the radiation
source and the cassette device by outputting the generated
synchronization control signal to the radiation source and the
cassette device.
22. A radiographic image capturing method comprising the steps of:
constructing a controller for controlling a cassette device, which
accommodates a radiation detector therein, and a radiation source
integrally with a camera, or constructing a radiation source
device, which accommodates the radiation source therein, integrally
with the camera; capturing an image of at least the cassette device
with the camera; transmitting an image of the cassette device
captured by the camera to a waiting location communication unit
provided in a waiting location where a doctor or radiological
technician having authority to apply the radiation to the subject
waits while being unable to see the subject directly; in a case
that a region to be imaged of the subject is included within the
image of the cassette device transmitted to the waiting location
communication unit, giving an instruction from the waiting location
communication unit to the radiation source to emit the radiation,
and thereby emitting the radiation from the radiation source and
applying the radiation to the subject; and detecting radiation that
has passed through the subject and the cassette device, and
converting the detected radiation into a radiographic image, with
the radiation detector.
Description
CROSS-REFERENCE TO RELATED APPLICATIONS AND PRIORITY CLAIMS
[0001] This application is a Continuation of International
Application No. PCT/JP2011/066405 filed on Jul. 20, 2011, which was
published under PCT Article 21(2) in Japanese, which is based upon
and claims the benefit of priority from Japanese Patent
Applications No. 2010-167255 filed on Jul. 26, 2010, and No.
2010-167257 filed on Jul. 26, 2010, the contents all of which are
incorporated herein by reference.
TECHNICAL FIELD
[0002] The present invention relates to a radiographic image
capturing apparatus (radiographic imaging device), a radiographic
image capturing system (radiographic imaging system), and a
radiographic image capturing method (radiographic imaging method)
for applying radiation from a radiation source to a subject,
detecting radiation that has passed through the subject with a
radiation detector, and converting the detected radiation into a
radiographic image.
BACKGROUND ART
[0003] In the medical field, there have widely been used
radiographic image capturing apparatus, which apply radiation to a
subject and guide radiation that has passed through the subject to
a radiation conversion panel (radiation detector) in order to
capture a radiographic image. Known forms of radiation conversion
panels include a conventional radiographic film for recording a
radiographic image by way of exposure, and a stimulable phosphor
panel for storing radiation energy representing a radiographic
image in a phosphor and emitting stimulated light representing the
radiographic image if the stimulable phosphor panel is irradiated
with stimulating light. The radiographic film with the recorded
radiographic image is supplied to an image developing device, which
develops the radiographic image. The stimulable phosphor panel is
supplied to an image reading device, which reads the radiographic
image from the stimulable phosphor panel as a visible image.
[0004] In an operating room or the like, it is necessary to read a
recorded radiographic image immediately from a radiation conversion
panel after the radiographic image has been captured for the
purpose of quickly and appropriately treating the patient. As a
radiation detector that meets such a requirement, there have been
developed a radiation detector of a direct conversion type having a
solid-state detector for converting radiation directly into an
electric signal, and a radiation detector of an indirect conversion
type having a scintillator for temporarily converting radiation
into visible light and a solid-state detector for converting the
visible light into an electric signal.
[0005] The radiation detector is housed in a radiation detecting
cassette (cassette device), which is permeable to radiation.
[0006] As disclosed in Japanese Laid-Open Patent Publication No.
2003-093354, such radiographic image capturing apparatus are
developed on the assumption that they will be used in order to
capture radiographic images of patients in hospitals.
[0007] There are potential demands for capturing radiographic
images outside of hospitals. To meet such demands, radiographic
image capturing apparatus, which are mounted on motor vehicles
dedicated for medical checkups, have been proposed in the art (see
Japanese Laid-Open Patent Publication No. 2008-206740). However,
such proposed radiographic image capturing apparatus mounted on
medical checkup motor vehicles are relatively large in size. Needs
have arisen for capturing radiographic images of persons suffering
from natural disasters at disaster sites, or persons who are
receiving home-care services in their homes. However, existing
medical checkup motor vehicles cannot be used in the former
applications as it is difficult to get them to disaster sites.
Although existing medical checkup motor vehicles may be driven to
homes of persons who are receiving home-care services, i.e., home
care treatment sites, the image capturing process is highly
burdensome to people to be imaged, because such people have to be
taken from their homes into the medical checkup motor vehicle in
order to capture radiographic images. Therefore, there have been
demands for small-size portable radiographic image capturing
apparatus for use at natural disaster sites or homes receiving
home-care services.
[0008] There has been developed a portable radiographic image
capturing apparatus, which can be folded into a compact form as a
whole, as disclosed in Japanese Laid-Open Patent Publication No.
11-104117.
SUMMARY OF INVENTION
Problems to be Solved by the Invention
[0009] If a radiographic image capturing apparatus is reduced in
overall size and weight, it becomes easy to carry around. A doctor
or radiological technician carries the radiographic image capturing
apparatus to a disaster site or a home care treatment site. At the
disaster site or the home care treatment site, the doctor or
radiological technician assembles the radiographic image capturing
apparatus and captures a radiographic image using the same.
[0010] Radiographic images can usually only be captured by doctors
or similarly qualified persons who are authorized as nationally
licensed practitioners. In Japan, for example, persons who are
legally permitted to engage in the business of applying radiation
to a human body (to capture a radiographic image of the human body)
are limited to doctors and dentists (hereinafter simply referred to
as "doctors") and medical radiological technicians (hereinafter
simply referred to as "radiological technicians") according to the
Radiology Technicians Act. If a doctor or radiological technician
who has legal authority concerning application of radiation to a
subject is unable to go to a disaster site or a home care treatment
site for some reason, then a person other than a doctor or
radiological technician, i.e., a person who is not qualified as a
medical radiological technician according to the Radiology
Technicians Act (hereinafter referred to as an "operator"), may
take a radiographic image capturing apparatus to the site and
perform a preparatory procedure to make the radiographic image
capturing apparatus ready to capture radiographic images, e.g., to
position a body region to be imaged of the subject with respect to
a cassette device of the radiation detector. However, such an
operator is not legally permitted to capture radiographic images of
the subject with the radiographic image capturing apparatus.
According to the present practice, a qualified person such as a
doctor or radiological technician needs to go to the disaster site
or the home care treatment site in order to capture radiographic
images of the subject with the radiographic image capturing
apparatus.
[0011] To eliminate the above shortcomings, the technologies
disclosed in Japanese Laid-Open Patent Publication No. 2003-093354
and Japanese Laid-Open Patent Publication No. 2008-206740 may be
applied in order to capture radiographic images of a subject,
according to instructions from a doctor or a radiological
technician who remains in a waiting location (e.g., a medical
organization or a medical checkup motor vehicle) where the doctor
or radiological technician cannot see the subject directly.
[0012] According to the technology disclosed in Japanese Laid-Open
Patent Publication No. 2003-093354, an image (radiographic image)
of an affected region of an emergency patient (subject) who has
been carried into a medical organization is sent to the mobile
terminal of a doctor who is not available at the medical
organization, and the doctor is asked to give instructions as to a
next radiographic image to be captured of the emergency patient. If
the technology disclosed in Japanese Laid-Open Patent Publication
No. 2003-093354 is applied directly, then the image of the affected
region of the emergency patient, which is sent to the mobile
terminal of the doctor in order to seek the doctor's instructions
as to a next radiographic image to be captured, may possibly be a
radiographic image that has been captured without the approval of
the doctor. In addition, since the image of the affected region of
the emergency patient needs to be sent to the mobile terminal of
the doctor in order to seek the doctor's instructions as to a next
radiographic image to be captured, the doctor is unable to instruct
a person at the site how to capture a radiographic image of the
patient in real time.
[0013] According to the technology disclosed in Japanese Laid-Open
Patent Publication No. 2008-206740, the exposure of a subject to
radiation is interrupted based on an optical image representing a
body movement of the subject. Even if the technology disclosed in
Japanese Laid-Open Patent Publication No. 2008-206740 were applied
directly, the doctor is unable to instruct a person at the site to
capture a radiographic image of the patient in real time.
Object of Invention
[0014] The present invention has been made in view of the above
problems. It is an object of the present invention to provide a
radiographic image capturing apparatus, a radiographic image
capturing system, and a radiographic image capturing method, which
are capable of capturing an image of a subject without requiring a
doctor or a radiological technician to travel directly to a
disaster site or a home care treatment site.
Configurations of Invention
[0015] To achieve the aforementioned objects, a radiographic image
capturing apparatus according to the present invention
comprises:
[0016] a radiation source for outputting radiation;
[0017] a radiation detector for detecting radiation that has passed
through a subject and converting the detected radiation into a
radiographic image upon application of the radiation to the subject
from the radiation source;
[0018] a cassette device that is permeable to the radiation and
accommodates the radiation detector therein;
[0019] a camera for capturing an image of at least the cassette
device; and
[0020] a camera image communication unit that transmits an image of
the cassette device captured by the camera to a waiting location
communication unit provided in a waiting location where a doctor or
radiological technician having authority to apply the radiation to
the subject waits while being unable to see the subject
directly,
[0021] wherein the camera is made integral with a controller for
controlling the radiation source and the cassette device, or is
made integral with a radiation source device accommodating the
radiation source therein.
[0022] Further, in order to achieve the aforementioned objects, a
radiographic image capturing system according to the present
invention comprises:
[0023] a radiographic image capturing apparatus having a radiation
source for outputting radiation, a radiation detector for detecting
radiation that has passed through a subject and converting the
detected radiation into a radiographic image upon application of
the radiation to the subject from the radiation source, a cassette
device that is permeable to the radiation and accommodates the
radiation detector therein, a camera for capturing an image of at
least the cassette device, and a camera image communication unit
that externally transmits an image of the cassette device captured
by the camera; and
[0024] a console and a waiting location communication unit which
are disposed at a waiting location where a doctor or radiological
technician having authority to apply the radiation to the subject
waits while being unable to see the subject directly, the waiting
location communication unit being adapted to receive an image of
the cassette device from the camera image communication unit, the
console being connected electrically to the waiting location
communication unit, the image of the cassette device being input
from the waiting location communication unit to the console,
[0025] wherein the camera is made integral with a controller of the
radiographic image capturing apparatus for controlling the
radiation source and the cassette device, or is made integral with
a radiation source device accommodating the radiation source
therein.
[0026] Furthermore, in order to achieve the aforementioned objects,
there is provided a radiographic image capturing method comprising
the steps of:
[0027] constructing a controller for controlling a cassette device,
which accommodates a radiation detector therein, and a radiation
source integrally with a camera, or constructing a radiation source
device, which accommodates the radiation source therein, integrally
with the camera;
[0028] capturing an image of at least the cassette device with the
camera;
[0029] transmitting an image of the cassette device captured by the
camera to a waiting location communication unit provided in a
waiting location where a doctor or radiological technician having
authority to apply the radiation to the subject waits while being
unable to see the subject directly;
[0030] in a case that a region to be imaged of the subject is
included within the image of the cassette device transmitted to the
waiting location communication unit, giving an instruction from the
waiting location communication unit to the radiation source to emit
the radiation, and thereby emitting the radiation from the
radiation source and applying the radiation to the subject; and
[0031] detecting radiation that has passed through the subject and
the cassette device, and converting the detected radiation into a
radiographic image, with the radiation detector.
Effect of Invention
[0032] According to the present invention, at a disaster site or a
home care treatment site, the camera, which is constructed
integrally with the controller or with the radiation source device,
captures an image of at least the cassette device. The camera image
communication unit transmits an image of the cassette device
captured by the camera to the waiting location communication unit,
which is disposed at the waiting location. Consequently, a doctor
or radiological technician, who is waiting at the waiting location
while unable to observe the subject directly, can provide
instructions to an operator of the radiographic image capturing
apparatus, who is currently at the disaster site or the home care
treatment site, for capturing an image of the subject in real time,
based on the image of the cassette device, which was received by
the waiting location communication unit. Accordingly, image
capturing can be carried out with respect to the subject, even
though the doctor or radiological technician cannot travel directly
to the disaster site or the home care treatment site.
BRIEF DESCRIPTION OF DRAWINGS
[0033] FIG. 1 is a perspective view of a radiographic image
capturing apparatus and a radiographic image capturing system
according to an exemplary embodiment of the present invention;
[0034] FIG. 2 is a perspective view of the radiographic image
capturing apparatus shown in FIG. 1;
[0035] FIG. 3 is a side elevational view of the radiographic image
capturing apparatus shown in FIGS. 1 and 2;
[0036] FIG. 4 is a side elevational view of the radiographic image
capturing apparatus shown in FIGS. 1 and 2;
[0037] FIG. 5 is a perspective view showing the manner in which the
radiographic image capturing apparatus shown in FIGS. 1 and 2 is
carried;
[0038] FIG. 6 is a view showing an internal structure of a
radiation source device shown in FIG. 1;
[0039] FIG. 7 is a plan view of a cassette device shown in FIGS. 1
and 2;
[0040] FIG. 8 is a view showing schematically a matrix made up of
pixels in a radiation detector;
[0041] FIG. 9 is a circuit diagram of the cassette device;
[0042] FIG. 10 is a block diagram of the radiographic image
capturing apparatus shown in FIG. 1;
[0043] FIG. 11 is a block diagram of a medical organization shown
in FIG. 1;
[0044] FIG. 12 is a flowchart for describing image capturing by the
radiographic image capturing apparatus and the radiographic image
capturing system shown in FIG. 1;
[0045] FIG. 13 is a flowchart for describing in greater detail
image capturing preparations carried out in step S5 of the
flowchart of FIG. 12;
[0046] FIGS. 14A to 14C are exemplary views of display screens of
at least one of a console and a portable information terminal;
[0047] FIGS. 15A to 15C are exemplary views of display screens of
at least one of a console and a portable information terminal;
[0048] FIG. 16 is a perspective view showing a manner in which a
portable information terminal, a radiation source device, and a
cassette device are charged in a medical organization;
[0049] FIG. 17 is a perspective view of a radiographic image
capturing apparatus and a radiographic image capturing system
according to a first modification;
[0050] FIG. 18 is a perspective view of a radiographic image
capturing apparatus and a radiographic image capturing system
according to a second modification;
[0051] FIG. 19 is a perspective view of a radiographic image
capturing apparatus and a radiographic image capturing system
according to a third modification;
[0052] FIG. 20 is a perspective view of a radiographic image
capturing apparatus and a radiographic image capturing system
according to a fourth modification;
[0053] FIG. 21 is a perspective view of a radiographic image
capturing apparatus and a radiographic image capturing system
according to a fifth modification;
[0054] FIG. 22 is a perspective view of a radiographic image
capturing apparatus and a radiographic image capturing system
according to a sixth modification;
[0055] FIG. 23 is a perspective view of a radiographic image
capturing apparatus and a radiographic image capturing system
according to a seventh modification;
[0056] FIG. 24 is a perspective view of a radiographic image
capturing apparatus and a radiographic image capturing system
according to an eighth modification;
[0057] FIG. 25 is a structural view of a radiographic image
capturing apparatus and a radiographic image capturing system
according to a ninth modification;
[0058] FIGS. 26A and 26B are partial structural views of a
radiographic image capturing apparatus and a radiographic image
capturing system according to a tenth modification;
[0059] FIGS. 27A and 27B are partial structural views of a
radiographic image capturing apparatus and a radiographic image
capturing system according to the tenth modification;
[0060] FIGS. 28A and 28B are partial structural views of a
radiographic image capturing apparatus and a radiographic image
capturing system according to the tenth modification;
[0061] FIGS. 29A and 29B are partial structural views of a
radiographic image capturing apparatus and a radiographic image
capturing system according to the tenth modification;
[0062] FIGS. 30A and 30B are partial structural views of a
radiographic image capturing apparatus and a radiographic image
capturing system according to the tenth modification;
[0063] FIG. 31A is a partial structural view of a radiographic
image capturing apparatus;
[0064] FIG. 31B is an exemplary view of a display screen of at
least one of a portable information terminal and a console in the
condition shown in FIG. 31A;
[0065] FIG. 32A is a partial structural view of a radiographic
image capturing apparatus;
[0066] FIG. 32B is an exemplary view of a display screen of at
least one of a portable information terminal and a console in the
condition shown in FIG. 32A;
[0067] FIG. 33A is an exemplary view of a display screen of at
least one of a portable information terminal and a console after
completion of image capturing in the condition shown in FIG.
31A;
[0068] FIG. 33B is an exemplary view of a display screen of at
least one of a portable information terminal and a console after
completion of image capturing in the condition shown in FIG.
32A;
[0069] FIG. 34 is a partial structural drawing of a radiographic
image capturing apparatus and a radiographic image capturing system
according to an eleventh modification;
[0070] FIG. 35 is a perspective view of a radiation source device
shown in FIG. 34;
[0071] FIGS. 36A and 36B are partial structural views of a
radiographic image capturing apparatus;
[0072] FIGS. 37A and 37B are perspective views showing other
configurations of the radiation source device of FIG. 35;
[0073] FIG. 38 is a partial structural drawing of a radiographic
image capturing apparatus and a radiographic image capturing system
according to a twelfth modification;
[0074] FIG. 39 is an explanatory drawing showing another
configuration of the radiographic image capturing apparatus and the
radiographic image capturing system of FIG. 38;
[0075] FIG. 40 is a partial structural drawing of a radiographic
image capturing apparatus and a radiographic image capturing system
according to a thirteenth modification;
[0076] FIG. 41A is an outline explanatory drawing showing
schematically an internal structure of a cassette device according
to a fourteenth modification; and
[0077] FIG. 41B is an outline explanatory drawing showing
schematically and by way of example a scintillator shown in FIG.
41A.
DESCRIPTION OF EMBODIMENTS
[0078] A radiographic image capturing apparatus and a radiographic
image capturing system including the radiographic image capturing
apparatus, according to a preferred exemplary embodiment of the
present invention, in relation to a radiographic image capturing
method, will be described in detail below with reference to FIGS. 1
through 41B.
Configurations of Embodiments
[0079] As shown in FIGS. 1 and 2, a radiographic image capturing
system 11 according to the present exemplary embodiment includes a
radiographic image capturing apparatus 10. The radiographic image
capturing apparatus 10 has a radiation source device 16, a cassette
device 22, and a portable information terminal 34 (controller,
PC).
[0080] The radiation source device 16 houses therein a radiation
source 14 for emitting radiation 12, and is made of a material that
is permeable to radiation 12. The cassette device 22 houses therein
a radiation detector 20 (see FIGS. 3 and 4) for converting
radiation 12 that has passed through a subject 18 into a
radiographic image, and is made of a material that is permeable to
radiation 12. The portable information terminal (controller, PC) 34
is electrically connected through a USB cable 24 to the radiation
source device 16, and is electrically connected through a USB cable
26 to the cassette device 22. Further, the portable information
terminal 34 accommodates therein a web camera 30 for capturing an
image of a prescribed image capturing region 28, and serves as a
portable terminal which can be operated by an operator 32 (see FIG.
5) of the radiographic image capturing apparatus 10. In this case,
the portable information terminal 34 is capable of sending signals
to and receiving signals from a medical organization 40 (waiting
location) to which a doctor (or radiological technician) 38
belongs, via a network 36 such as a public network or the like by
way of wireless communications.
[0081] Radiographic images can usually be captured only by doctors
or similarly qualified persons who are authorized as nationally
licensed practitioners. The operator 32 refers to a person who is
not qualified as a medical radiological technician according to the
Radiology Technicians Act of Japan, or more specifically, a person
other than doctors and dentists (hereinafter simply referred to as
"doctors") and medical radiological technicians (hereinafter simply
referred to as "radiological technicians") who have legal authority
to apply radiation 12 to the subject 18.
[0082] Further, according to the present exemplary embodiment, the
subject 18 is present at a disaster site or a home care treatment
site, whereas the doctor (or radiological technician) 38 is present
(waits) in a (remote) medical organization 40 where the doctor 38
is unable to see the subject 18 directly. The doctor 38 is unable
to go to the disaster site or the home care treatment site for
certain reasons, whereas the operator 32 travels to the disaster
site or the home care treatment site in lieu of the doctor 38.
Hereinafter, reference numeral 38 will be used to represent a
doctor.
[0083] As shown in FIGS. 1 through 4 and 7, the cassette device 22
includes a substantially rectangular housing 42 made of a material
permeable to radiation 12. The housing 42 includes a surface,
referred to as an irradiated surface 44, which faces toward the
radiation source device 16 and is irradiated with radiation 12. The
cassette device 22 is formed with guide lines 46 disposed within an
irradiated area (irradiated field), which is irradiated with
radiation 12, of the irradiated surface 44, and which serves as a
reference for an image capturing area and an image capturing
position. The guide lines 46 provide an outer frame (irradiated
field of radiation 12), which as shown in FIG. 7, is substantially
aligned with the outer edge of the radiation detector 20 as viewed
in plan. Further, on one side surface 48 of the housing 42, a
switch 50 is arranged for activating the cassette device 22, and a
connector 52 of the USB cable 26 is connected thereto.
[0084] As shown in FIGS. 3 and 6, the radiation source device 16
has a substantially cylindrical casing 130 made of a material
permeable to radiation 12. In this case, the casing 130 of the
radiation source device 16 houses therein, in addition to the
radiation source 14, an irradiated field lamp 56 for emitting
irradiation light 54. The irradiated field lamp 56 applies
irradiation light 54 to the irradiated surface 44 before the
radiation source 14 outputs radiation 12, thereby illuminating the
irradiated field of the radiation 12 on the irradiated surface
44.
[0085] It is assumed that a straight line interconnecting a focus
point 160, to be described later, of the radiation source 14 and a
central position of the guide lines 46, i.e., a point of
intersection between the criss-crossing guide lines 46, is
substantially perpendicular to the irradiated surface 44 (see FIGS.
1, 2, and 7). If the distance (imaging distance) between the focus
point 160 and the central position of the criss-crossing guide
lines 46 is set to a source-to-image distance (SID), then the outer
edge of the irradiated field, which is displayed on the irradiated
surface 44 upon application of irradiation light 54 thereto,
essentially is aligned with the outer frame of the guide lines 46.
Further, the location of the casing 130 through which the
irradiation light 54 passes preferably is made of a material
permeable to the irradiation light 54, for example. Furthermore, as
shown in FIGS. 1, 2 and 6, a connector 58 of the USB cable 24 is
connected to a side surface of the casing 130.
[0086] As shown in FIGS. 1 through 4 and 16, the portable
information terminal 34 comprises a notebook-sized personal
computer (PC) including an operating unit 60 such as a keyboard,
etc., disposed on an upper surface (facing a lid 66) of a main body
62, and a display unit 64 such as a display or the like is disposed
on a lower surface (facing the operating unit 60) of the lid 66.
With the present embodiment, a description is given of a notebook
type portable information terminal 34. However, the portable
information terminal 34 may be a different type of portable
terminal having various functions, including the operating unit 60,
the display unit 64, etc., such as a mobile phone or a PDA
(personal information terminal).
[0087] During times that the portable information terminal 34 is
not in use, the main body 62 and the lid 66 are folded over one
another about a shaft 68 on one side of the main body 62 and two
hinges 70 connected to respective ends of the shaft 68, as shown in
FIG. 16. The upper surface of the main body 62 has two teeth 72,
and the lower surface of the lid 66 has two recesses 74
corresponding respectively to the two teeth 72. If the upper
surface of the main body 62 and the lower surface of the lid 66 are
brought into contact with each other at a time that the portable
information terminal 34 is not in use, the teeth 72 are fitted
respectively into the recesses 74, thereby keeping the main body 62
and the lid 66 folded over each other.
[0088] During times that the portable information terminal 34 is in
use, the lid 66 is turned away from the main body 62 about the
shaft 68 and the hinges 70, thereby unfolding the main body 62 and
the lid 66 away from each other, from the folded position shown in
FIG. 16 to the operational position shown in FIGS. 1 through 4.
[0089] On the upper surface of the main body 62 in the vicinity of
the operating unit 60, there are provided a power supply switch 76
for activating the portable information terminal 34, speakers
(audio output unit) 78 for outputting speech sounds, and a
microphone 80 for detecting voices of the subject 18 and the
operator 32.
[0090] Further, USB terminals 84, 88, 90, a card slot 94, and an AC
adapter input terminal 96 are provided on a side surface of the
main body 62. A connector 82 of the USB cable 24 is fitted into the
USB terminal 84. A connector 86 of the USB cable 26 is fitted into
the USB terminal 88. By fitting of a connector of a non-illustrated
USB cable into the USB terminal 90, information can be transmitted
to and received from an external device through the USB cable. A
memory card 92 is cable of being mounted in the card slot 94.
[0091] On the other hand, on the upper surface of the lid 66, a web
camera 30 is arranged as an optical camera. Accordingly, the web
camera 30 is constructed integrally with the portable information
terminal 34.
[0092] Integral construction between the web camera 30 and the
portable information terminal 34 is not limited to the structures
shown in FIGS. 1 through 4, in which the web camera 30 is
incorporated in the portable information terminal 34, but includes
a structure in which, at least at times that the radiographic image
capturing apparatus 10 is in use, the web camera 30 and the
portable information terminal 34 are joined (connected) together in
an integral manner.
[0093] Therefore, the web camera 30 may be made integral with the
portable information terminal 34 in any one of the following
situations (1) through (3). (1) The web camera 30 is connected to
the portable information terminal 34 by a cable, which is included
in the radiographic image capturing apparatus 10. (2) The web
camera 30 is connected to the portable information terminal 34 by a
cable, which is provided by the operator 32. (3) During times that
the radiographic image capturing apparatus 10 is in use, the
portable information terminal 34 is coupled to the web camera 30,
and during times that the radiographic image capturing apparatus 10
is serviced for maintenance or is not in use, the web camera 30 can
be spaced (or separated) from the portable information terminal
34.
[0094] In order to enable the web camera 30 to be spaced from the
portable information terminal 34 during times that the radiographic
image capturing apparatus 10 is serviced for maintenance or is not
in use, for example, the web camera 30 may be coupled to the
portable information terminal 34 by a coupling means such as a clip
or the like. The web camera 30 is coupled to the portable
information terminal 34 by the coupling means only at times that
the radiographic image capturing apparatus 10 is in use. Further,
the coupling means may incorporate a ball joint to facilitate
coupling of the web camera 30 to the portable information terminal
34 and to change the orientation thereof freely. If the web camera
30 is coupled to the portable information terminal 34 by way of
such a coupling means, the web camera 30 and the portable
information terminal 34 must be connected to each other through a
wired link (e.g., a USB cable) or a wireless link.
[0095] If the web camera 30 and the portable information terminal
34 are connected to each other by a cable, then since the web
camera 30 can independently be placed in a desired position within
the range permitted by the length of the cable, the web camera 30
can be positioned with greater freedom than if the web camera 30
were incorporated in the portable information terminal 34.
[0096] Concerning the web camera 30, by turning the lid 66 with
respect to the main body 62, the upper surface of the lid 66 is
made to face toward the cassette device 22, the radiation source
device 16, and the subject 18, and further, if the operator 32
turns on the power supply switch 76 thereby energizing the portable
information terminal 34, an image is captured as an image capturing
region 28 at least of the irradiated region (region within the
guide lines 46) of the radiation 12. More preferably, as shown in
FIGS. 1 through 4, in a state in which the subject 18 is positioned
between the radiation source device 16 and the cassette device 22,
the web camera 30 captures as an image capturing region 28 a
predetermined region including the radiation source device 16, the
subject 18, and the cassette device 22.
[0097] In this case, the web camera 30 continuously captures an
optical image of the image capturing region 28, and outputs a
camera image (moving image) which is representative of the
continuously captured optical image. The web camera 30 can also
(intermittently) capture optical images of the image capturing
region 28 at given time intervals, and output a camera image (still
image) representative of the intermittently captured optical image
or a camera image (still image) captured at a certain time.
[0098] FIG. 5 shows a state of the radiographic image capturing
apparatus 10, at a time that the radiographic image capturing
apparatus 10 is carried by the operator 32. During times that the
radiographic image capturing apparatus 10 is carried by the
operator 32, the radiation source device 16, the cassette device
22, and the folded portable information terminal 34 are housed in
an attache case 98, in a state in which the connectors 52, 58, 82,
86 (see FIGS. 1 and 2) are taken out, and the electrical
connections by the USB cables are disconnected. Thus, the operator
32 can grip the handle 100 and carry the attache case 98 from the
medical organization 40 to a desired location, e.g., a disaster
site or a home care treatment site. Accordingly, at the location
where the attache case 98 is carried, the operator 32 can remove
the radiation source device 16, the cassette device 22, and the
folded portable information terminal 34 from the attache case 98,
and assemble these components into the configuration shown in FIGS.
1 through 4. The operator 32 can then perform a preparatory
procedure in order to ready the radiographic image capturing
apparatus 10 for capturing radiographic images of a disaster victim
at a disaster site or a home-care-service recipient at a home care
treatment site.
[0099] In this manner, the radiographic image capturing apparatus
10 according to the present exemplary embodiment can be referred to
as a portable radiographic image capturing apparatus, in which the
web camera 30 and the portable information terminal 34 are made
integral with each other. The disaster victim or the
home-care-service recipient, who is a subject to be imaged in order
to produce a radiographic image thereof, will hereinafter be
referred to as the subject 18.
[0100] Returning to FIG. 1, the medical organization 40 includes a
communication unit (waiting location communication unit, wireless
communication unit) 104 having an antenna 102 for sending signals
to and receiving signals from the portable information terminal 34
via the network 36 by way of wireless communications. A console 106
is electrically connected to the communication unit 104.
[0101] The console 106 is connected to a radiology information
system (RIS), not shown, which generally manages radiographic
images and other information that are handled in a radiological
department of the medical organization 40. The RIS is connected to
a hospital information system (HIS), not shown, which generally
manages medical information in the medical organization 40.
[0102] The console 106 is placed on a desk 107 in a room where a
doctor 38 in the medical organization 40 is present.
[0103] The console 106 comprises a main body 108 for carrying out
various processing sequences, a display unit 112, an operating unit
114, a web camera 116, a speaker 118 for outputting speech sounds,
an exposure switch 120, and a microphone 122 capable of inputting
the voice of the doctor 38 thereto.
[0104] The display unit 112 is a display for displaying
predetermined images and information for the doctor 38, who is
seated in a chair 110 at the desk 107. The operating unit 114 is a
keyboard or the like, which is operated by the doctor 38. The web
camera 116 is mounted on an upper end of the display unit 112 for
capturing an image of the doctor 38. The exposure switch 120 can be
turned on by the doctor 38 in order to initiate emission of
radiation 12 from the radiation source 14.
[0105] As described above, the portable information terminal 34 and
the communication unit 104 send signals to and receive signals from
each other via the network 36 by way of wireless
communications.
[0106] For this purpose, the portable information terminal 34 is
capable of sending camera images output from the web camera 30, a
radiographic image supplied via the USB cable 26 from the cassette
device 22 (radiation detector 20), and voice signals representative
of voices of the operator 32 or the subject 18 input to the
microphone 80, through the antenna 102 of the medical organization
40 to the communication unit 104 via the network 36 by way of
wireless communications.
[0107] On the other hand, the communication unit 104 is capable of
sending a camera image (a moving image, still images captured
intermittently, or still images captured at predetermined times) of
the doctor 38 captured by the web camera 116, an exposure control
signal generated in the main body 108 based on the doctor 38
turning on the exposure switch 120, and a voice signal representing
the voice of the doctor 38 input to the microphone 122, to the
portable information terminal 34 via the antenna 102 and the
network 36 by way of wireless communications.
[0108] The display unit 64 of the portable information terminal 34
is capable of displaying at least one of a camera image of the
image capturing region 28 captured by the web camera 30, a
radiographic image from the radiation detector 20, and a camera
image of the doctor 38 captured by the web camera 116. The display
unit 64 also is capable of displaying information (character
information) corresponding to the voice and exposure control
signals referred to above. Moreover, the speakers 78 are capable of
outputting the voice of the doctor 38, and a sound that depends on
the exposure control signal (an alarm sound indicative of the start
of emission of radiation 12 from the radiation source 14).
[0109] The portable information terminal 34 sends a synchronization
control signal, which is generated based on the exposure control
signal, to the radiation source device 16 and the cassette device
22 via the USB cables 24, 26, for thereby synchronizing (start of)
emission of radiation 12 from the radiation source 14 and detection
and conversion of radiation 12 into a radiographic image in the
radiation detector 20 with each other.
[0110] On the other hand, on the console 106, similar to the case
of the display unit 64, the display unit 112 is capable of
displaying at least one of a camera image in the image capturing
region 28 captured by the web camera 30, a radiographic image from
the radiation detector 20, and a camera image of the doctor 38
captured by the web camera 116. The display unit 112 also is
capable of displaying information (character information)
corresponding to the voice and exposure control signals referred to
above. Moreover, the speaker 118 is capable of outputting voices of
the operator 32 or the subject 18 and sounds depending on the
exposure control signal.
[0111] Internal structural details of the radiation source device
16 and the cassette device 22 will be described in specific detail
below with reference to FIGS. 6 through 9.
[0112] As shown in FIG. 6, in the interior of the radiation source
device 16, there are accommodated the radiation source 14, the
irradiated field lamp 56, the USB terminal 132 in which the
connector 58 of the USB cable 24 is fitted, a battery 134, a
communication unit (radiation source communication unit) 136, a
radiation source controller 138 for controlling the radiation
source 14, a mirror 144 made of a material permeable to radiation
12, and a collimator 146, which is made of a material impermeable
to radiation 12 but is permeable to the irradiation light 54. The
battery 134 can be charged from an external source (e.g., the
portable information terminal 34) via the USB cable 24, the
connector 58, and the USB terminal 132, and is capable of supplying
electric power to various components in the radiation source device
16.
[0113] The radiation source 14 comprises a field-emission-type
radiation source.
[0114] More specifically, the radiation source 14 includes a
disk-shaped rotary anode 152 mounted on a rotational shaft 150,
which can be rotated about its axis through a rotating mechanism
148, an annular target layer 154 disposed on the surface of the
rotary anode 152 and which is made mainly of a metallic element
such as Mo or the like, a cathode 156 disposed in confronting
relation to the rotary anode 152, and a field-emission-type
electron source 158 disposed on the cathode 156 in confronting
relation to the target layer 154.
[0115] The radiation source controller 138 controls the radiation
source 14 in order to output radiation 12 according to a
synchronization control signal based on an exposure control signal,
which is received from the portable information terminal 34 (see
FIGS. 1 through 5) via the USB cable 24, the connector 58, the USB
terminal 132, and the communication unit 136.
[0116] More specifically, the radiation source 14 is controlled by
the radiation source controller 138 to output radiation 12 in the
following manner. The rotating mechanism 148 rotates the rotational
shaft 150 to thereby rotate the rotary anode 152. The battery 134
supplies electric power to a power supply 142, which applies a
voltage (negative voltage) to the field-emission-type electron
source 158. The battery 134 also supplies electric power to a power
supply 140, which applies a voltage between the rotary anode 152
and the cathode 156, i.e., the power supply 140 applies a positive
voltage to the rotary anode 152 and a negative voltage to the
cathode 156.
[0117] The field-emission-type electron source 158 emits electrons,
which are accelerated to bombard the target layer 154 under the
voltage applied between the rotary anode 152 and the cathode 156.
The bombarded surface (focus point 160) of the target layer 154
emits radiation 12 at an intensity level depending on the applied
electrons. Radiation 12 passes through the mirror 144, the
irradiation area thereof is constricted by the collimator 146, and
radiation 12 is output from the radiation source device 16.
[0118] Until the radiation source controller 138 is supplied with
the synchronization control signal from the portable information
terminal 34, the radiation source controller 138 controls the
irradiated field lamp 56 in order to emit irradiation light 54. The
irradiation light 54 emitted from the irradiated field lamp 56 is
reflected by the mirror 144 in the direction of the collimator 146,
and is output from the radiation source device 16.
[0119] As shown in FIGS. 3, 4 and 7, the cassette device 22 houses
therein a grid 162 for removing scattered rays of radiation 12 from
the subject 18 if the radiation source 14 applies radiation 12 to
the subject 18, the radiation detector 20, and a lead plate 164 for
absorbing back scattered rays of radiation 12, which are
successively arranged in this order from the irradiated surface 44
of the cassette device 22, which faces toward the subject 18. The
irradiated surface 44 of the cassette device 22 may be constructed
as the grid 162.
[0120] The radiation detector 20 may comprise an indirect
conversion type of radiation detector including a scintillator for
converting radiation 12 having passed through the subject 18 into
visible light, and solid-state detectors (hereinafter also referred
to as pixels) made of amorphous silicon (a-Si) or the like for
converting visible light into electric signals, or a direct
conversion type of radiation detector comprising solid-state
detectors made of amorphous selenium (a-Se) or the like for
converting the dose of radiation 12 directly into electric
signals.
[0121] The aforementioned switch 50 and the USB terminal 172 with
which the connector 52 of the USB cable 26 is fitted are disposed
on the side surface 48 of the cassette device 22.
[0122] Furthermore, the cassette device 22 also houses therein a
battery 166, a cassette controller 168, and a communication unit
170.
[0123] The battery 166, which is chargeable from an external device
(e.g., the portable information terminal 34) through the USB cable
26, the connector 52 and the USB terminal 172, supplies electric
power to various components (the radiation detector 20, the
cassette controller 168, the communication unit 170) of the
cassette device 22. The cassette controller 168 controls the
radiation detector 20 with electric power supplied from the battery
166. The communication unit 170 sends and receives signals,
including information of the radiation 12 detected by the radiation
detector 20, to and from the portable information terminal 34 by
way of the USB terminal 172, the connector 52, and the USB cable
26.
[0124] A plate of lead or the like preferably is placed over the
side surfaces of the cassette controller 168 and the communication
unit 170 under the irradiated surface 44, so as to protect the
cassette controller 168 and the communication unit 170 against
damage, which otherwise would be caused if these components were
irradiated with radiation 12.
[0125] As schematically shown in FIG. 8, the radiation detector 20
comprises a number of pixels 180 arrayed on a substrate, not shown,
a number of gate lines 182 for supplying control signals to the
pixels 180, and a number of signal lines 184 for reading electric
signals output from the pixels 180.
[0126] A circuit arrangement of the cassette device 22, which
incorporates an indirect conversion type of radiation detector 20,
for example, will be described in detail below with reference to
FIG. 9.
[0127] As shown in FIG. 9, the radiation detector 20 comprises an
array of TFTs 188 arranged in rows and columns, and a photoelectric
conversion layer 186 including pixels 180 and made of a material
such as amorphous silicon (a-Si) or the like for converting visible
light into electric signals. The photoelectric conversion layer 186
is disposed on the array of TFTs 188. If radiation 12 is applied to
the radiation detector 20, the pixels 180, which are supplied with
a bias voltage Vb from the battery 166, generate electric charges
by converting visible light into electric signals (analog signals).
The TFTs 188 are turned on along each row at a time, whereupon the
electric charges can be read out from the pixels 180 as an image
signal.
[0128] The TFTs 188 are connected to the respective pixels 180. The
gate lines 182, which extend parallel to the rows, and the signal
lines 184, which extend parallel to the columns, are connected to
the TFTs 188. The gate lines 182 are connected to a line scanning
driver 190, and the signal lines 184 are connected to a multiplexer
192. The gate lines 182 are supplied with control signals Von, Voff
from the line scanning driver 190 for turning on and off the TFTs
188 along the rows. The line scanning driver 190 comprises a
plurality of switches SW1 for switching between the gate lines 182,
and an address decoder 194 for outputting a selection signal for
selecting one of the switches SW1 at a time. The address decoder
194 is supplied with an address signal from the cassette controller
168.
[0129] The signal lines 184 are supplied with electric charges that
are stored by the pixels 180 through the TFTs 188 arranged in
columns. Electric charges supplied to the signal lines 184 are
amplified by amplifiers 196, which are connected respectively to
the signal lines 184. The amplifiers 196 are connected to the
multiplexer 192 through respective sample and hold circuits 198.
The multiplexer 192 comprises a plurality of switches SW2 for
successively switching between the signal lines 184, and an address
decoder 200 for outputting selection signals for selecting one of
the switches SW2 at a time. The address decoder 200 is supplied
with address signals from the cassette controller 168. The
multiplexer 192 has an output terminal connected to an A/D
converter 202. A radiographic image signal, which is generated by
the multiplexer 192 based on electric charges from the sample and
hold circuits 198, is converted by the A/D converter 202 into a
digital image signal representing radiographic image information,
which is supplied to the cassette controller 168.
[0130] The TFTs 188, which function as switching devices, may be
combined with another image capturing device such as a CMOS
(Complementary Metal-Oxide Semiconductor) image sensor or the like.
Alternatively, the TFTs 188 may be replaced with a CCD
(Charge-Coupled Device) image sensor for shifting and transferring
electric charges by way of shift pulses, which correspond to gate
signals in the TFTs.
[0131] FIG. 10 shows in block form the radiographic image capturing
apparatus 10, and FIG. 11 shows in block form the medical
organization 40.
[0132] In FIGS. 10 and 11, constituent elements that have not been
described above with reference to FIGS. 1 through 9 will be
described in further detail, together with portions of the
constituent elements that were described in FIGS. 1 through 9.
[0133] The cassette controller 168 of the cassette device 22
comprises an image memory 210, an address signal generator 212, and
a cassette ID memory 214.
[0134] The address signal generator 212 supplies address signals to
the address decoder 194 of the line scanning driver 190, and to the
address decoder 200 of the multiplexer 192. The image memory 210
stores radiographic images detected by the radiation detector 20.
The cassette ID memory 214 stores cassette ID information for
identifying (the cassette device 22 of) the radiographic image
capturing apparatus 10.
[0135] In this case, the cassette controller 168 sends the cassette
ID information stored in the cassette ID memory 214, and the
radiographic image information stored in the image memory 210 to
the portable information terminal 34 from the communication unit
170 via the USB terminal 172 and the USB cable 26.
[0136] The portable information terminal 34 further includes a
communication unit (controller communication unit, camera image
communication unit) 218, a battery 220 for supplying electric power
to various components of the portable information terminal 34, a
control processor 222 for performing various control processes, and
a memory 224 for storing camera images, radiographic images,
etc.
[0137] The communication unit 218 sends signals to and receives
signals from the exterior by way of wireless communications via an
antenna 216, sends signals to and receives signals from the
exterior by way of wired communications via the USB terminals 84,
88, 90, and sends signals to and receives signals from the memory
card 92, which is inserted in the card slot 94.
[0138] If the operator 32 turns on the power supply switch 76, the
battery 220 supplies electric power to the web camera 30, the
speakers 78, the microphone 80, the communication unit 218, and the
control processor 222. Further, while the portable information
terminal 34 is electrically connected by the USB cables 24, 26
respectively to the radiation source device 16 and the cassette
device 22, the battery 220 is capable of charging the batteries
134, 166 respectively via the USB cables 24, 26. Moreover, the
battery 220 can also be charged from the exterior via the input
terminal 96.
[0139] More specifically, in the foregoing manner, with the
portable information terminal 34 electrically connected by the USB
cable 24 to the radiation source device 16, electric power can be
supplied and signals can be sent and received (transmitted) between
the portable information terminal 34 and the radiation source
device 16 by way of wired communications. Further, with the
portable information terminal 34 electrically connected by the USB
cable 26 to the cassette device 22, electric power can be supplied
and signals can be sent and received (transmitted) between the
portable information terminal 34 and the cassette device 22 by way
of wired communications.
[0140] The control processor 222 comprises a CPU of the portable
information terminal 34, which carries out various control
sequences by reading and executing programs stored in the memory
224.
[0141] More specifically, the control processor 222 stores in the
memory 224 camera images captured by the web camera 30 together
with radiographic images and cassette ID information received from
the cassette device 22 via the USB cable 26 and the communication
unit 218, and together therewith, the control processor 222
controls the display unit 64 to display at least one of the camera
images and the radiographic images. Further, the control processor
222 sends at least one of the camera images, and the radiographic
images and the cassette ID information by way of wireless
communications to the medical organization 40 via the communication
unit 218, the antenna 216, and the network 36. In addition, the
control processor 222 sends a voice signal representing the voice
of the operator 32 or the voice of the subject 18 input to the
microphone 80 by way of wireless communications to the medical
organization 40 via the communication unit 218, the antenna 216,
and the network 36.
[0142] Further, the control processor 222 controls the display unit
64 to display a camera image (of the doctor 38) captured by the web
camera 116 and received from the medical organization 40 via the
network 36, the antenna 216, and the communication unit 218, and
outputs the voice of the doctor 38 from the speaker 78 based on the
voice signal received from the medical organization 40.
Furthermore, in the case that the control processor 222 receives an
exposure control signal from the medical organization 40, the
control processor 222 generates a synchronization control signal
depending on the received exposure control signal, and sends the
generated synchronization control signal to the radiation source
device 16 and the cassette device 22 via the USB cable 24, 26.
Accordingly, synchronization can be realized between output of
radiation 12 from the radiation source 14 and detection and
conversion of the radiation 12 into radiographic image information
by the radiation detector 20.
[0143] The console 106 also includes a memory 228 and a control
processor 226 for performing various control sequences.
[0144] The control processor 226 comprises a CPU of the main body
108, which carries out various control sequences by reading and
executing programs stored in the memory 228.
[0145] More specifically, the control processor 226 stores the
camera image captured by the web camera 116 in the memory 228,
together with displaying the camera image on the display unit 112.
Further, the control processor 226 sends the camera image captured
by the web camera 116 to the portable information terminal 34 by
way of wireless communications via the communication unit 104, the
antenna 102, and the network 36. The control processor 226 also
sends a voice signal representing the voice of the doctor 38 input
to the microphone 122 to the portable information terminal 34 by
way of wireless communications via the communication unit 104, the
antenna 102, and the network 36.
[0146] Further, the control processor 226 stores in the memory 228
at least one of the camera image that was transmitted wirelessly
from the portable information terminal 34, and the radiographic
image and cassette ID information, together with displaying at
least one of the camera image and the radiographic image on the
display unit 112. Furthermore, the control processor 226 outputs
from the speaker 118 the voice signal representing the voice of the
operator 32 or the subject 18 that was transmitted wirelessly from
the portable information terminal 34.
[0147] Further, prior to output of radiation 12 from the radiation
source 14 (in the image capturing preparatory stage), if a region
to be imaged of the subject 18 is visible within the outer frame of
the guide lines 46 on a camera image captured by the web camera 30
and displayed on the display unit 112 (see FIGS. 14A and 14B), then
the doctor 38 judges that an appropriate radiographic image of the
region to be imaged of the subject 18 can be acquired if radiation
were applied to the subject in this state, whereupon the doctor 38
turns on the exposure switch 120. Based on turning on of the
exposure switch 120, the control processor 226 generates an
exposure control signal for initiating output of radiation 12 from
the radiation source 14, and the generated exposure control signal
is transmitted to the portable information terminal 34 by way of
wireless communications via the communication unit 104, the antenna
102, and the network 36.
[0148] On the other hand, prior to output of radiation 12 from the
radiation source 14, if the region to be imaged of the subject 18
is not visible, or if only a portion of the region is included
within the outer frame of the guide lines 46 on a camera image
captured by the web camera 30 and displayed on the display unit 112
(see FIG. 14C), then the doctor 38 judges that an appropriate
radiographic image of the region to be imaged of the subject 18
cannot be acquired by applying radiation 12 to the subject 18 in
this condition. In this case, next, the doctor 38, without turning
on the exposure switch 120, issues an instruction by voice over the
microphone 122 to change the position or posture of the subject 18
so that the region to be imaged is included within the outer frame
of the guide lines 46. Accordingly, in the case that such a voice
signal (instruction signal) is input corresponding to the voice
from the microphone 122, the control processor 226 does not
generate an exposure control signal.
[Operations of the Present Exemplary Embodiment]
[0149] The radiographic image capturing apparatus 10 and the
radiographic image capturing system 11 according to the present
exemplary embodiment basically are constructed as described above.
Next, operations (a radiographic image capturing method) thereof
will be described below with reference to the flowcharts shown in
FIGS. 12 and 13. In explaining such operations, FIGS. 1 through 11
may also be referred to as needed.
[0150] In step S1 shown in FIG. 12, the operator 32 (see FIG. 5)
carries an attache case 98 from the medical organization 40, where
the doctor 38 is unable to observe the subject 18 directly, to a
disaster site or a home care treatment site, according to
directions from the doctor 38 who has legal authority to apply
radiation 12 to the subject 18 (see FIGS. 1 through 4 and FIG.
10).
[0151] In step S2, after the operator 32 has arrived at the
disaster site or the home care treatment site, at first, the
operator 32 removes the radiation source device 16, the cassette
device 22, the portable information terminal 34, and the USB cables
24, 26 from the attache case 98. Then, the operator 32 connects the
portable information terminal 34 and the radiation source device 16
using the USB cable 24, and connects the portable information
terminal 34 and the cassette device 22 using the USB cable 26. As a
result, the portable information terminal 34 and the radiation
source device 16 are connected electrically via the USB cable 24,
whereas the portable information terminal 34 and the cassette
device 22 are connected electrically via the USB cable 26. Further,
in step S2, the operator lays out the portable information terminal
34, the radiation source device 16 and the cassette device 22
according to the positional relationship shown in FIGS. 1 through
4.
[0152] In the following step S3, the operator 32 turns the lid 66
away from the main body 62 about the shaft 68 and the hinges 70, so
as to unfold the portable information terminal 34 from the folded
condition shown in FIGS. 5 and 16, and until the operating unit 60
and the display unit 64 are made visible, as shown in FIGS. 1
through 4. Thereafter, the operator 32 turns on the power supply
switch 76 in order to activate the portable information terminal
34.
[0153] In this manner, by turning on the power supply switch 76,
the battery 220 begins supplying electric power to the web camera
30, the display unit 64, the microphone 80, the communication unit
218, and the control processor 222. Further, the battery 220 begins
to charge the battery 134 of the radiation source device 16 and the
battery 166 of the cassette device 22 from the USB terminals 84, 88
through the USB cables 24, 26. As a result, the web camera 30 is
activated by supply of power from the battery 220 and starts to
capture an image of the image capturing region 28. The captured
camera image is output to the control processor 222 (step S4).
[0154] On the other hand, by supply of power from the battery 220,
the control processor 222 reads and executes the program from the
memory 224. Owing thereto, the control processor 222 stores the
camera image input from the web camera 30 in the memory 224, and
displays the camera image on the display unit 64. Further, the
control processor 222 transmits the camera image from the
communication unit 218 to the exterior by way of wireless
communications via the antenna 216.
[0155] The camera image from the web camera 30 is sent to the
medical organization 40 by way of wireless communications over the
network 36. The communication unit 104 of the medical organization
40 outputs to the control processor 226 the camera image received
via the antenna 102. The control processor 226 reads and executes
the program stored in the memory 228, whereby the camera image
input from the web camera 30 is stored in the memory 228, together
with displaying the camera image on the display unit 112. Upon
viewing the content displayed on the display unit 112, the doctor
38 can reliably grasp the positional relationship between the
radiation source device 16, the subject 18, and the cassette device
22 at the disaster site or the home care treatment site.
[0156] Next, in step S5, the operator 32 performs image capturing
preparations for capturing a radiographic image of a region to be
imaged (for example, a chest region) of the subject 18.
[0157] FIG. 13 is a flowchart for describing in greater detail
image capturing preparations carried out in step S5. FIGS. 14A to
14C are exemplary views of display content, which is displayed on
the display unit 64 of the portable information terminal 34 or the
display unit 112 of the console 106 during image capturing
preparations.
[0158] In step S51 of FIG. 13, the operator 32 operates the
operating unit 60 (see FIGS. 1 and 10) of the portable information
terminal 34, whereby subject information such as image capturing
conditions (e.g., a tube voltage and tube current of the radiation
source 14, an exposure time of the radiation 12) or the like
pertaining to the subject 18 to be imaged are registered. In this
case, if the region to be imaged and the imaging method are known
beforehand, the operator 32 may also register such image capturing
conditions in advance. The control processor 222 stores (registers)
the input image capturing conditions in the memory 224.
[0159] In the event that the subject 18 to be imaged is known ahead
of time before leaving for the disaster site or the home care
treatment site, the operator 32 can enter and register the image
capturing conditions by operating the operating unit 60 of the
portable information terminal 34 at the medical organization 40 to
which the operator 32 belongs.
[0160] Further, as described previously, because transmission and
reception of signals wirelessly over the network 36 can be
performed between the portable information terminal 34 and the
medical organization 40, for example, the doctor 38 may input the
aforementioned image capturing conditions by operating the
operating unit 114 of the console 106, and the input image
capturing conditions may be sent wirelessly to the portable
information terminal 34 over the network 36. Alternatively,
suitable image capturing conditions to be recorded in the memory
224 may be indicated from the medical organization 40 (the doctor
38) by way of wireless communications over the network 36. Further,
by the operator 32 operating the operating unit 60, the image
capturing conditions, which were indicated by way of wireless
communications, can be registered.
[0161] If the operator 32 turns on the switch 50 of the cassette
device 22 in the following step S52, the battery 166 supplies
electric power to the radiation detector 20, the cassette
controller 168, and the communication unit 170, thereby activating
the cassette device 22 in its entirety. Consequently, the cassette
controller 168 sends an activation notice signal, which indicates
that the cassette device 22 has been activated, to the portable
information terminal 34 by way of the communication unit 170, the
USB terminal 172, and the USB cable 26.
[0162] Based on the activation notice signal received via the USB
cable 26, the USB terminal 88, and the communication unit 218, the
control processor 222 sends an image capturing preparation command
signal for image capturing preparations, and the image capturing
conditions registered in the memory 224 to the radiation source
device 16 and the cassette device 22 by way of the communication
unit 218, the USB terminals 84, 88, and the USB cables 24, 26.
[0163] The battery 134 of the radiation source device 16
continuously supplies electric power to the communication unit 136
and the radiation source controller 138. Therefore, if the
radiation source controller 138 receives the image capturing
preparation command signal and the image capturing conditions by
way of the USB cable 24, the USB terminal 132 and the communication
unit 136, the radiation source controller 138 registers the image
capturing conditions, and then controls the battery 134 to supply
electric power to the irradiated field lamp 56. Upon supplying the
irradiated field lamp 56 with the electric power from the battery
134, the irradiated field lamp 56 emits irradiation light 54 (see
FIGS. 3, 4, and 6). The irradiation light 54 is reflected by the
mirror 144 toward the collimator 146, and is applied to the
irradiated surface 44 of the cassette device 22 (step S53).
[0164] If the imaging distance is adjusted to the SID, then the
irradiated field of radiation 12 that is displayed on the
irradiated surface 44 by application of the irradiation light 54 is
substantially in agreement with the outer frame of the guide lines
46. On the other hand, if the position of the irradiated field
(i.e., the range irradiated by the irradiation light 54) is not in
agreement with the position of the outer frame of the guide lines
46, or if the size of the irradiated field is not in agreement with
the size of the outer frame of the guide lines 46, then the
operator 32 adjusts the positional relationship between the
radiation source device 16 and the cassette device 22 in order to
bring the imaging distance and the SID into agreement with each
other.
[0165] The image capturing preparation command signal and the image
capturing conditions also are sent to the cassette device 22, so as
to enable the cassette controller 168 to recognize that the
radiographic image capturing apparatus 10 has been in an image
capturing preparation stage, and also to register image capturing
conditions in the cassette ID memory 214. Further, it has been
described above that the radiation detector 20 is activated by
turning on the switch 50. However, the battery 166 may also supply
electric power (bias voltage Vb) to the radiation detector 20 in
order to activate the radiation detector 20 upon receipt of the
image capturing preparation command signal by the cassette
controller 168.
[0166] In the foregoing manner, the image capturing distance is
adjusted to the SID, and in step S54, after the irradiation field
of the radiation 12 and the outer frame of the guide lines 46 have
been brought into agreement with each other, the operator 32
arranges the subject 18 on the side of the irradiated surface 44 of
the cassette device 22, and carries out positioning the subject 18
so that the region to be imaged of the subject 18 is positioned
inside the outer frame of the guide lines 46.
[0167] In this case, the web camera 30 captures an image of the
image capturing region 28 (see FIGS. 1 through 4) including the
region to be imaged of the subject 18, the radiation source device
16, and the irradiated surface 44 of the cassette device 22, and
the display unit 64 of the portable information terminal 34
displays the camera image captured by the web camera 30.
Accordingly, while the operator 32 observes (monitors) the camera
image displayed on the display unit 64, by giving instructions to
the subject 18, the subject 18 can be positioned so that in the
camera image the region to be imaged lies within the outer frame of
the guide lines 46.
[0168] Further, the camera image captured by the web camera 30 is
transmitted (delivered) to the medical organization 40 from the
control processor 222 via the communication unit 218, the antenna
216, and the network 36. The communication unit 104 of the medical
organization 40 outputs the camera image received over the antenna
102 to the console 106. The control processor 226 of the console
106 stores the camera image in the memory 228 and displays the
camera image on the display unit 112.
[0169] In addition, in step S6 of FIG. 12, the doctor 38 of the
medical organization 40 (see FIGS. 1 and 11) visually confirms the
camera images from the web camera 30 (see FIGS. 1 through 4 and 10)
displayed on the display unit 112, and judges whether or not the
image capturing preparations for the subject 18 have been
completed, and more specifically, whether or not the region to be
imaged of the subject 18 is visible within the outer frame of the
guide lines 46 in the camera image.
[0170] For example, as shown in FIG. 14A, in the case that the
camera image displayed on the display units 64, 112 is an image in
which the region to be imaged (the chest) is visible within the
outer frame of the guide lines 46, the doctor 38 judges that an
appropriate radiographic image of the subject 18 would be obtained
if an image were captured having the positional relationship
between the guide lines 46 and the region to be imaged presently
displayed on the screens of the display units 64, 112 (step S6:
YES). Thereafter, the doctor 38, by way of voice using the
microphone 122, or by operating the operating unit 114, conveys to
the operator 32 at the site that image capturing preparations are
completed.
[0171] In this manner, the control processor 226 of the console 106
sends the voice signal input to the microphone 122 or a signal
generated by the operating unit 114 to the portable information
terminal 34 by way of wireless communications via the communication
unit 104, the antenna 102, and the network 36. Based on the signal
received via the antenna 216 and the communication unit 218, the
control processor 222 of the portable information terminal 34
displays the characters "POSITIONING IS OK" on the display unit 64,
thereby indicating that image capturing preparations have been
completed, as shown in FIG. 14A. Alternatively, the control
processor 222 may inform the operator 32 of completion of image
capturing preparations by outputting speech sounds from the
speakers 78. Therefore, the operator 32 can grasp that image
capturing preparations have been completed by confirming the
display content of the display unit 64, or by hearing the speech
sounds from the speakers 78.
[0172] Further, the web camera 116 of the console 106 captures an
image of the doctor 38, and the control processor 226 also sends
the camera image from the web camera 116 to the portable
information terminal 34 over the communication unit 104, the
antenna 102 and the network 36. Owing thereto, as shown in FIG.
14B, the control processor 222 may display both alongside each
other on the screen of the display unit 64 the camera image of the
web camera 30 (the image showing positioning of the subject 18) and
the camera image of the web camera 116 (the image of the doctor
38). At this time, the control processor 222 may also display on
the screen of the display unit 64 the characters "POSITIONING IS
OK" together with the camera image from the web camera 116.
[0173] In this manner, by displaying the image of the doctor 38 on
the screen of the display unit 64, and by visually confirming the
display content of the display unit 64, the operator 32 can
comprehend immediately that the doctor 38 has confirmed the camera
image of the web camera 30 and has approved capturing of an image
with the present positioning of the subject 18 (i.e., has provided
an indication that image capturing preparations are completed.)
[0174] Further, along with displaying the images of FIGS. 14A and
14B, the doctor 38 may cause a voice instruction input to the
microphone 122 to be output from the speaker 78. Furthermore,
similar to the display unit 64, display of images (refer to FIG.
14A or FIG. 14B) may also be performed on the display unit 112.
[0175] On the other hand, in step S6, if the camera image of the
web camera 30 displayed on the display unit 112 indicates that the
region to be imaged of the subject 18 is not included within the
outer frame of the guide lines 46 (see FIG. 14C), or that only a
portion of the region to be imaged is included therein, then the
doctor 38 determines that a desired radiographic image of the
subject 18 cannot be produced by capturing a radiographic image in
the positional relationship between the guide lines 46 and the
region to be imaged that is currently displayed on the screens of
the display units 64, 112 (step S6: NO). Then, using the microphone
122 to enter a voice signal or by operating the operating unit 114,
the doctor 38 conveys to the operator 32 at the site that the
positional relationship between the region to be imaged and the
guide lines 46 is inappropriate, and therefore that image capturing
preparations must be performed again.
[0176] In this manner, the control processor 226 of the console 106
sends the voice signal input to the microphone 122 or a signal
(instruction signal) generated by operating the operating unit 114
to the portable information terminal 34 by way of wireless
communications via the communication unit 104, the antenna 102, and
the network 36. Based on the signal received via the antenna 216
and the communication unit 218, the control processor 222 of the
portable information terminal 34 displays the characters
"MOVE/REPOSITION PATIENT ON CASSETTE" on the display unit 64, as
shown in FIG. 14C, indicating that image capturing preparations
must be performed again. Alternatively, speech sounds may be output
from the speakers 78. Therefore, the operator 32 can grasp
immediately that image capturing preparations must be repeated and
the subject 18 must be positioned again, by confirming the content
displayed on the display unit 64, or by hearing the speech sounds
from the speakers 78.
[0177] In the case that the image capturing preparations of step S5
are to be repeated, since the processes of steps S51 to S53 (see
FIG. 13) have already been performed, the operator 32 merely
repeats and performs positioning of the subject 18 again.
[0178] In addition, in step S7, based on the assumption that image
capturing preparations have been completed (step S6: YES), the
doctor 38 turns on the exposure switch 120. As a result, the
control processor 226 generates an exposure control signal to start
emission of radiation 12 from the radiation source 14, and sends
the exposure control signal to the portable information terminal 34
via the communication unit 104, the antenna 102, and the network
36.
[0179] If the control processor 222 receives the exposure control
signal via the antenna 216 and the communication unit 218, the
control processor 222 generates a synchronization control signal
for capturing a radiographic image of the subject 18 by
synchronizing start of emission of radiation 12 from the radiation
source 14 with detection and conversion of radiation 12 into a
radiographic image in the radiation detector 20. The generated
synchronization control signal is sent to the radiation source
device 16 and the cassette device 22 via the communication unit
218, the USB terminals 84, 88, and the USB cables 24, 26.
[0180] In step S8, upon the radiation source controller 138 (see
FIGS. 6 and 10) receiving the synchronization control signal
through the USB terminal 132 and the communication unit 136, the
radiation source controller 138 stops supplying electric power from
the battery 134 to the irradiated field lamp 56, thereby
de-energizing the irradiated field lamp 56 and stopping emission of
irradiation light 54, and together therewith, the radiation source
controller 138 controls the radiation source 14 to apply radiation
12 at a predetermined dose to the subject 18 according to the image
capturing conditions registered in the radiation source controller
138.
[0181] In this manner, in the radiation source 14, the rotating
mechanism 148 is controlled by the radiation source controller 138
to rotate the rotational shaft 150 and the rotary anode 152. The
power supply 142 applies a negative voltage to the
field-emission-type electron source 158 based on electric power
supplied from the battery 134, and the power supply 140 applies a
voltage between the rotary anode 152 and the cathode 156 based on
electric power supplied from the battery 134. The
field-emission-type electron source 158 emits electrons, which are
accelerated by the voltage applied between the rotary anode 152 and
the cathode 156 and bombard the target layer 154. The surface of
the target layer 154 that is bombarded with electrons (the focus
point 160) emits radiation 12, the intensity of which depends on
the applied electrons.
[0182] Radiation 12 passes through the mirror 144 and the
irradiation area thereof is constricted by the collimator 146,
after which radiation 12 is output from the radiation source device
16 and applied to the subject 18. Radiation 12 is applied to and
passes through the subject 18 for a given exposure time depending
on the image capturing conditions, and reaches the radiation
detector 20 in the cassette device 22.
[0183] In step S9, since the radiation detector 20 (see FIGS. 3, 4,
and FIGS. 7 through 10) is of an indirect conversion type, the
scintillator of the radiation detector 20 emits visible light
having an intensity that depends on the intensity of the radiation
12. The pixels 180 of the photoelectric conversion layer 186
convert visible light into electric signals and store the electric
signals as electric charges. The electric charges stored by the
pixels 180, which are representative of a radiographic image of the
subject 18, are read from the pixels 180 according to address
signals, which are supplied from the address signal generator 212
of the cassette controller 168 to the line scanning driver 190 and
the multiplexer 192.
[0184] More specifically, in response to the address signal
supplied from the address signal generator 212, the address decoder
194 of the line scanning driver 190 outputs a selection signal to
select one of the switches SW1, which supplies the control signal
Von to the gates of the TFTs 188 connected to the gate line 182
corresponding to the selected switch SW1. In response to the
address signal supplied from the address signal generator 212, the
address decoder 200 of the multiplexer 192 outputs a selection
signal to successively turn on the switches SW2, so as to switch
between the signal lines 184 for thereby reading, through the
signal lines 184, the electric charges stored in the pixels 180
connected to the selected gate line 182.
[0185] The radiographic image read from the pixels 180 connected to
the selected gate line 182 is amplified by the respective
amplifiers 196, sampled by the sample and hold circuits 198, and
supplied via the multiplexer 192 to the A/D converter 202 and
converted into digital signals. The converted digital signals,
which are representative of the radiographic image, are stored in
the image memory 210 of the cassette controller 168 (step S10).
[0186] Similarly, the address decoder 194 of the line scanning
driver 190 successively turns on the switches SW1 in order to
switch between the gate lines 182 according to address signals
supplied from the address signal generator 212. The electric
charges stored in the pixels 180 connected to the successively
selected gate lines 182 are read through the signal lines 184, and
are processed into digital signals by the multiplexer 192 and the
A/D converter 202, whereupon the digital signals are stored in the
image memory 210 of the cassette controller 168 (step S10).
[0187] The radiographic image stored in the image memory 210 is
transmitted together with the cassette ID information stored in the
cassette ID memory 214 to the portable information terminal 34 by
way of wired communications via the communication unit 170, the USB
terminal 172, and the USB cable 26. The control processor 222 of
the portable information terminal 34 stores the radiographic image
and the cassette ID information received via the USB terminal 88
and the communication unit 218 in the memory 224, and displays the
radiographic image on the display unit 64 (refer to step S11 and
FIG. 15A).
[0188] Further, the control processor 222 transmits the
radiographic image and the cassette ID information to the medical
organization 40 wirelessly via the communication unit 218, the
antenna 216, and the network 36. Consequently, in the medical
organization 40, the communication unit 104 outputs the
radiographic image and the cassette ID information received via the
antenna 102 to the control processor 226, whereupon the control
processor 226 stores the radiographic image and the cassette ID
information in the memory 228 together with displaying the
radiographic image on the display unit 112 (see FIG. 15A).
[0189] In step S12, the doctor 38 visually confirms the
radiographic image displayed on the display unit 112 and judges
whether or not an appropriate radiographic image of the subject 18
has been obtained.
[0190] For example, if as shown in FIG. 15A, the radiographic image
displayed on the display units 64, 112 is an image that includes
the region to be imaged (the chest region) of the subject 18, the
doctor 38 determines that image capturing of the radiographic image
with respect to the region to be imaged has been completed properly
(step S12: YES). Next, the doctor 38, by way of a voice message
using the microphone 122, or by operating the operating unit 114,
conveys to the operator 32 at the site that image capturing has
been completed.
[0191] As a result, the control processor 226 of the console 106
sends the voice message input to the microphone 122, or a signal
responsive to operations performed using the operating unit 114, to
the portable information terminal 34 by way of wireless
communications via the communication unit 104, the antenna 102, and
the network 36. Based on the signal received via the antenna 216
and the communication unit 218, the control processor 222 of the
portable information terminal 34 displays on the display unit 64
the characters "IMAGE CAPTURING IS COMPLETED" as shown in FIG. 15A,
or alternatively outputs a voice message from the speaker 78, to
indicate completion of image capturing. Accordingly, by visually
confirming the content displayed on the display unit 64, or by
listening to the voice message from the speaker 78, the operator 32
can grasp that image capturing has been completed.
[0192] Further, similar to the case of FIG. 14B, as shown in FIG.
15B, the control processor 222 may display alongside each other the
radiographic image and the camera image (of the doctor) from the
web camera 116 on the screen of the display unit 64, along with
displaying the characters "IMAGE CAPTURING IS COMPLETED" in the
camera image from the web camera 116.
[0193] By displaying in tandem the image of the doctor 38 on the
screen of the display unit 64, the operator 32 can understand
immediately that the doctor 38 has indicated completion of image
capturing.
[0194] Further, together with the image displays of FIG. 15A and
FIG. 15B, a voice message of the doctor 38 input to the microphone
122 can be output from the speaker 78, or a display image similar
to that of the display unit 64 (see FIG. 15A or 15B) can be
performed on the display unit 112.
[0195] On the other hand, in step S12, in the case that the region
to be imaged is not visible within the radiographic image displayed
on the display unit 112, or if only a portion of the region to be
imaged is included therein (see FIG. 15C), the doctor 38 judges
that an appropriate radiographic image could not be obtained and
that image recapturing is necessary (step S12: NO). In this case,
by a voice message using the microphone 122, or by operating the
operating unit 114, the doctor 38 conveys to the operator 32 at the
site that the image needs to be captured again.
[0196] As a result, the control processor 226 of the console 106
transmits wirelessly to the portable information terminal 34, via
the communication unit 104, the antenna 102, and the network 36,
the voice message input to the microphone 122, or a signal
indicative of the content entered using the operating unit 114.
Based on the signal received via the antenna 216 and the
communication unit 218, as shown in FIG. 15C, the control processor
222 of the portable information terminal 34 displays on the display
unit 64 the characters "IMAGE CAPTURING IS NO GOOD, PLEASE REPEAT
IMAGE CAPTURING", or outputs a corresponding voice message from the
speaker 78 for indicating image-recapturing. Consequently, by
visually confirming the content displayed on the display unit 64,
or by listening to the voice message from the speaker 78, the
operator 32 grasps that image capturing should be carried out
again, and returning to step S5, performs the image capturing
preparations again according to the instruction content.
[0197] In step S13, after completion of image capturing, the
operator 32 operates the operating unit 60 or presses the power
supply switch 76 in order to shut off the portable information
terminal 34, whereupon the battery 220 stops supplying electric
power from the battery 220 to various components in the portable
information terminal 34, and charging of the batteries 134, 166
from the battery 220 via the USB cables 24, 26 also is halted. The
radiation source controller 138 detects cessation of charging of
the battery 134, and halts the supply of power from the battery 134
to various components in the radiation source device 16.
Furthermore, by pressing the switch 50, the operator 32 turns off
the cassette device 22. As a result, supply of power from the
battery 166 to various components in the cassette device 22 is
halted.
[0198] Next, the operator 32 turns the lid 66 toward the main body
62 about the hinges 70 and the shaft 68 of the portable information
terminal 34, thereby bringing the teeth 72 into the recesses 74 and
folding the portable information terminal 34.
[0199] Next, the operator 32 removes the USB cables 24, 26 from the
radiation source device 16, the cassette device 22, and the
portable information terminal 34. As a result, electrical
connection between the portable information terminal 34 and the
radiation source device 16, and electrical connection between the
portable information terminal 34 and the cassette device 22 are
disconnected.
[0200] Thereafter, the operator 32 places the radiation source
device 16, the cassette device 22, the portable information
terminal 34, and the USB cables 24, 26 in the attache case 98 (step
S14), and the operator 32 carries the attache case 98 back to the
medical organization 40 to which the operator 32 belongs.
[0201] At the medical organization 40, radiographic images stored
in the memory 224 of the radiographic image capturing apparatus 10
carried back by the operator 32 are transmitted to the console 106
or the RIS of the hospital network by way of wireless
communications via the communication unit 218 and the antenna 216,
or by wired communications via the USB terminals 84, 88, 90.
Alternatively, the radiographic images are stored in a memory card
92, after storage thereof the memory card 92 is removed from the
card slot 94, and the radiographic images are read out from the
memory card 92 and supplied to the RIS. Consequently, in the
medical organization 40, detailed radiographic image diagnosis can
be implemented on the radiographic images.
[0202] As described above, in a state in which the radiographic
image capturing apparatus 10 is laid out at a disaster site or a
home care treatment site, radiographic images, etc., are
transmitted to the medical organization 40 from the portable
information terminal 34 via the network 36. Therefore, at the
medical organization 40, detailed image diagnosis can be carried
out using radiographic images sent from the site.
[Advantages of the Present Exemplary Embodiment]
[0203] As described above, with the radiographic image capturing
apparatus 10, the radiographic image capturing system 11, and the
radiographic image capturing method according to the present
exemplary embodiment, at a disaster site or a home care treatment
site, the web camera 30, which is constructed integrally with the
portable information terminal 34 (incorporated in the portable
information terminal 34), captures an image at least of the
cassette device 22 (the guide lines 46 corresponding to the
radiation detector 20 accommodated therein), whereas the
communication unit 218 transmits the camera image captured by the
web camera 30 through the network 36 to the communication unit 104
provided at the medical organization 40.
[0204] Owing thereto, based on the camera image received by the
communication unit 104, a doctor (or radiological technician) 38
who waits at the (remote) medical organization 40 while being
unable to observe the subject 18 directly can provide instructions
for capturing an image of the subject 18 in real time to the
operator 32 of the radiographic image capturing apparatus 10 at a
disaster site or a home care treatment site. Therefore, even if the
doctor 38 cannot travel directly to the disaster site or the home
care treatment site, i.e., even without accompanying the operator
32 who does not possess a license as a radiographic technician
(i.e., who is not qualified to apply radiation 12 to the subject
18), capturing of images with respect to the subject 18 can still
be carried out.
[0205] In this case, the outer frame of the guide lines 46
corresponds to the irradiated field of radiation 12 at the time
that the image capturing distance was set to the SID, and the web
camera 30 captures an image of the outer frame of the guide lines
46. Accordingly, the doctor 38 observes the camera image from the
web camera 30, and assuming that the region to be imaged of the
subject 18 lies within the outer frame of the guide lines 46 (i.e.,
is imaged inside of the guide lines 46), it can be judged that a
suitable radiographic image will be captured by irradiating the
subject 18 with radiation 12. On the other hand, in the event that
the region to be irradiated of the subject 18 is distanced from or
lies outside of the guide lines 46, or if only a portion of the
region to be imaged lies within the guide lines 46, in this
condition, the doctor 38 can judge that a desired radiographic
image cannot be obtained if the subject 18 is irradiated with
radiation 12.
[0206] In this manner, the web camera 30 captures an image of the
guide lines 46, and while observing (monitoring) the camera image
from the web camera 30, the doctor 38 judges whether or not the
region to be imaged of the subject 18 is included within the guide
lines 46, whereby it can be determined whether or not an
appropriate radiographic image can be obtained. As a result, even
if the doctor 38 cannot directly observe the subject 18 and the
operator 32, appropriate instructions for image capturing
preparations can be given to the operator 32 at the site.
[0207] Further, as noted previously, the web camera 30 is
incorporated into an upper side surface of the lid 66 of the
portable information terminal 34, and is constructed integrally
with the portable information terminal 34. In this case, as shown
in FIGS. 1 through 4, because the web camera 30 captures an image
of the radiation source device 16, the subject 18, and the cassette
device 22 including the guide lines 46, a camera image that
includes the guide lines 46 therein can reliably be captured.
[0208] Further, while operating the portable information terminal
34, the operator 32 instructs the subject 18 to position the
subject 18 with respect to the guide lines 46. Even if radiation 12
is applied from the radiation source 14 to the subject 18 while the
operator 32 operates the portable information terminal 34, the
operator 32 is reliably prevented from being exposed to radiation
12.
[0209] The communication unit 218 of the portable information
terminal 34, which incorporates the web camera 30, sends a camera
image to the medical organization 40 via the antenna 216 and the
network 36. Consequently, the camera image can reliably be sent to
the medical organization 40.
[0210] In this case, the control processor 222 of the portable
information terminal 34 generates a synchronization control signal,
which synchronizes with each other output of radiation 12 from the
radiation source 14, and conversion of the radiation 12 into a
radiographic image in the radiation detector 20. The communication
unit 218 sends the synchronization control signal to the
communication unit 136 of the radiation source device 16 and to the
communication unit 170 of the cassette device 22. Therefore, the
radiation source 14 and the radiation detector 20 can reliably be
synchronized during times that radiographic images are being
captured.
[0211] Further, because the portable information terminal 34, the
radiation source device 16, and the cassette device 22 are
connected electrically via the USB cables 24, 26, the battery 134
of the radiation source device 16 or the battery 166 of the
cassette device 22 can reliably be charged from the battery 220 of
the portable information terminal 34, together with reliably
performing transmission and reception of signals therebetween. More
specifically, transmission of image capturing conditions or
synchronization control signals from the portable information
terminal 34 to the radiation source device 16 and the cassette
device 22, as well as transmission of radiographic images from the
cassette device 22 to the portable information terminal 34 can
reliably be carried out.
[0212] Furthermore, inasmuch as the camera image captured by the
web camera 30 and the radiographic image are sent from the portable
information terminal 34 to the medical organization 40 by way of
wireless communications via the network 36, the doctor 38 at the
medical organization 40 can give appropriate instructions to the
operator 32 and the subject 18 at the site by visually recognizing
the camera image and the radiographic image, which are displayed on
the display unit 112 of the console 106.
[0213] Further, the console 106 includes the exposure switch 120
for initiating output of radiation 12 from the radiation source 14.
In this case, if the doctor 38 turns on the exposure switch 120
based on the camera image displayed on the display unit 112, the
control processor 226 of the console 106 generates an exposure
control signal for initiating output of radiation 12 from the
radiation source 14, and sends the generated exposure control
signal from the communication unit 104 to the portable information
terminal 34 via the network 36. Thus, the control processor 222 of
the portable information terminal 34 generates a synchronization
control signal based on the exposure control signal received by the
communication unit 218, and sends the generated synchronization
control signal to the radiation source device 16 and the cassette
device 22.
[0214] Consequently, the doctor 38 can capture a radiographic image
of the subject 18 in real time while monitoring the subject 18 at
the medical organization 40 where the doctor 38 is unable to
observe the subject 18 directly, without requiring the doctor 38 to
travel to the disaster site or the home care treatment site.
[0215] More specifically, in a case where image capturing
preparations have been completed, if the region to be imaged of the
subject 18 is included within the outer frame of the guide lines 46
as shown in the camera image captured by the web camera 30, the
doctor 38 turns on the exposure switch 120 to start capturing a
radiographic image of the subject 18. On the other hand, if the
region to be imaged of the subject 18 is not included within the
outer frame of the guide lines 46 in the camera image, or if only a
portion of the region to be imaged is included within the outer
frame of the guide lines 46 in the camera image, the doctor 38 does
not turn on the exposure switch 120, but instead instructs the
operator 32 to carry out image capturing preparations once
again.
[0216] Thus, an image capturing process can easily and reliably be
performed under remote control from the medical organization
40.
[0217] The doctor 38 instructs the operator 32 at the site through
screens, which are displayed on the display unit 64, and via speech
sounds, which are output from the speakers 78. Accordingly, the
doctor 38 can accurately and efficiently send instructions to the
operator 32 at the site.
[0218] If the camera images output from the web camera 30 are
moving images, or still images that are captured intermittently at
given time intervals, the doctor 38 can provide timely instructions
to the operator 32 at the site. Even if the camera images are still
images captured at certain times during image capturing
preparations, the doctor 38 can judge whether or not the subject 18
is in a state that enables radiographic images to be captured by
observing the still images.
[0219] If the web camera 30 is an optical camera, then the web
camera 30 can produce camera images that are easily and highly
visible to the doctor 38.
[0220] It has been described above that the doctor 38 provides
instructions to the operator 32 both through screens that are
displayed on the display unit 64 and via speech sounds that are
output from the speakers 78. However, the doctor 38 may provide
instructions to the operator 32 only through the screens displayed
on the display unit 64, or only via speech sounds output from the
speakers 78.
[0221] It also has been described above that the doctor 38 gives
instructions to the operator 32, and that the operator 32 positions
the subject 18 according to the content of such instructions. Since
speech sounds output from the speakers 78 are heard by the subject
18, the doctor 38 may send instructions directly to the subject 18
in order to position the subject 18. Alternatively, before the
subject 18 is positioned, the subject 18 may confirm the content of
such instructions, which are displayed on the display unit 64, and
the subject 18 may position him or herself with respect to the
guide lines according to the instructions.
[0222] It also has been described above that the portable
information terminal 34 sends the synchronization control signal to
the radiation source device 16 and the cassette device 22 via the
USB cables 24, 26. However, instead, the control processor 226 of
the console 106 may generate a synchronization control signal, and
may send the generated synchronization control signal to the
radiation source device 16 and the cassette device 22 via the
network 36, the portable information terminal 34, and the USB
cables 24, 26.
[0223] Still further, rather than activating the cassette device 22
by turning on the switch 50, the operator 32 may activate the
cassette device 22 by operating the operating unit 60.
Alternatively, the doctor 38 may activate the cassette device 22 by
operating the operating unit 114.
[0224] A case has been described above in which the battery 220
charges the batteries 134, 166 in a state of electrical connection
of the portable information terminal 34 to the radiation source
device 16 and the cassette device 22 via the USB cables 24, 26.
However, in place of this configuration, in a case where the
batteries 134, 166 are charged, the batteries 134, 166 may be
charged to a capacity that is large enough to capture at least as
many radiographic images of the subject 18 as required.
Accordingly, a required number of radiographic images of the
subject 18 can reliably be captured.
[0225] Alternatively, the batteries 134, 166 may be charged only
during a time period required for performing steps S3 through S7 of
FIG. 12. Thus, since the batteries 134, 166 are not charged while
radiographic images are being sent during and after radiographic
images are being captured, while image capturing is carried out,
noise caused by battery charging is prevented from being added to
the electric charge signals (analog signals), or while the
radiographic images are being sent, such noise can be prevented
from being added to the radiographic images.
[0226] It has been described above that a radiographic image begins
to be captured if the exposure switch 120 is turned on. However,
since a radiographic image may start to be captured by an
instruction from the doctor 38, an exposure button (exposure
switch) may be displayed on the screen of the display unit 112,
which is a touch panel display unit, for example, and the doctor 38
may press the displayed exposure button to start capturing a
radiographic image. Alternatively, one button on the operating unit
114 may be used as a dedicated exposure switch, whereby a
radiographic image starts to be captured by pressing the
button.
[0227] The cassette device 22 is in the shape of a box. However, a
portion of the cassette device 22 where the radiation detector 20,
etc., is positioned may be in the shape of a flexible sheet. Since
the flexible sheet can be wound into a roll, the overall
radiographic image capturing apparatus 10 including the cassette
device 22 can be reduced in size and weight.
[0228] Further, during image capturing, the radiation source device
16 and the cassette device 22 are fixed in predetermined positions
by non-illustrated fixing members, however, at least during image
capturing, the operator 32 may hold the radiation source device 16
by hand.
[0229] Although a case has been described above in which the
batteries 134, 166 are charged from the battery 220, any one of the
three batteries may be regarded as a power supply for the overall
radiographic image capturing apparatus 10, which is capable of
charging the other two remaining batteries.
[0230] Still further, it has been described above that the camera
image captured by the web camera 30 is sent from the communication
unit 218 of the portable information terminal 34 to the
communication unit 104 of the medical organization 40 via the
network 36. However, the present exemplary embodiment is not
limited to such a configuration.
[0231] For example, the communication unit 136 of the radiation
source device 16 and the communication unit 170 of the cassette
device 22 may include a function for communicating with the
communication unit 104 via the network 36, whereby camera images
can be sent from the communication units 136, 170.
[0232] By providing the communicating function so as to be
incorporated in the communication units 136, 170, it is possible
for the communication unit 170 to send radiographic images directly
to the communication unit 104 via the network 36, and also to send
radiographic images to the communication unit 104 via the
communication unit 136 and the network 36.
[0233] Furthermore, all of the signals may be sent and received
between the radiographic image capturing apparatus 10 and the
medical organization 40 through the communication units 136, 104 or
through the communication units 170, 104.
[0234] Moreover, as described above, signals are sent and received
between the radiographic image capturing apparatus 10 and the
medical organization 40 via the network 36 by way of wireless
communications. However, the present exemplary embodiment is not
limited to such a configuration. Signals may be sent and received
by way of other forms of communication.
[0235] More specifically, signals may be sent and received between
the radiographic image capturing apparatus 10 and the medical
organization 40 by way of wired communications via the network
36.
[0236] Alternatively, signals may be sent and received by way of
wired and wireless communications via the network 36. More
specifically, if the network 36 includes a repeater (repeating
device), then signals may be sent and received by way of wired
communications (or wireless communications) up to the repeater, and
then sent and received by way of wireless communications (or wired
communications) beyond the repeater.
[0237] Further, another portable terminal such as a mobile
telephone or the like may be electrically connected to the portable
information terminal 34. Signals may be sent and received between
the portable information terminal 34 and the medical organization
40, or may be sent and received between the radiation source device
16 and the cassette device 22, using a communication function of
the other portable terminal. According to this modification, the
communication unit of the other portable terminal functions as the
communication unit 218.
[0238] The present exemplary embodiment is applicable to
acquisition of radiographic images using a light readout type of
radiation detector. Such a light readout type radiation detector
operates in the following manner. If radiation is applied to a
matrix of solid-state detecting devices, the solid-state detecting
devices store an electrostatic latent image depending on the dose
of radiation applied thereto. For reading the stored electrostatic
latent image, reading light is applied to the solid-state detecting
devices to cause the solid-state detecting devices to generate an
electric current representing a radiographic image. If erasing
light is applied to the radiation detector, a radiographic image
represented by the residual electrostatic latent image is erased
from the radiation detector, which can be reused (see Japanese
Laid-Open Patent Publication No. 2000-105297).
[0239] Still further, in order to prevent the radiographic image
capturing apparatus 10 from being contaminated with blood and
bacteria, the entire radiographic image capturing apparatus 10 may
be of a water-resistant and hermetically sealed structure, and the
radiographic image capturing apparatus 10 can be sterilized and
cleaned as necessary so that it can be used repeatedly.
[0240] In the present exemplary embodiment, as shown in FIG. 16, a
cradle 230 for charging the batteries 134, 166, 220 (see FIG. 10)
is positioned at a desired location in the medical organization
40.
[0241] In this case, the cradle 230 is electrically connected to
the portable information terminal 34 by a USB cable 234 having
connectors 236, 238. Further, the cradle 230 is electrically
connected to the radiation source device 16 by a USB cable 24.
Moreover, the cradle 230 is electrically connected to the cassette
device 22 by a USB cable 26.
[0242] The cradle 230 may be capable not only of charging the
batteries 134, 166, 220, but may also have a wireless or wired
communication function to send and receive necessary information to
and from the console 106 and the RIS of the medical organization
40. Information that is sent from the cradle 230 may include
radiographic images, which are recorded in the radiographic image
capturing apparatus 10 that is connected to the cradle 230.
[0243] The cradle 230 has a display unit 232 for displaying a
charged state of the radiographic image capturing apparatus 10
connected to the cradle 230, together with other necessary
information including radiographic images acquired from the
radiographic image capturing apparatus 10.
[0244] A plurality of cradles 230 may be connected to a network,
and charged states of radiographic image capturing apparatus 10,
which are connected to the cradles 230, may be retrieved through
the network, so that the user can confirm the locations of
radiographic image capturing apparatus 10 that are charged
sufficiently based on the retrieved charged stages.
[0245] The radiographic image capturing apparatus 10 according to
the present exemplary embodiment has been illustrated as being used
to capture radiographic images at disaster sites and home care
treatment sites. However, the radiographic image capturing
apparatus 10 according to the present exemplary embodiment is not
limited to capturing radiographic images at disaster sites and home
care treatment sites. Alternatively, the radiographic image
capturing apparatus 10 may be mounted on medical checkup cars for
capturing radiographic images for use in medical checkups, or may
be used to capture radiographic images of patients during a
doctor's rounds in the medical organization 40. Furthermore, the
radiographic image capturing apparatus 10 according to the present
exemplary embodiment is not limited to being used for capturing
radiographic images in the medical field, but may be applied to
capturing radiographic images in various nondestructive tests, for
example.
[Modifications of the Present Exemplary Embodiment]
[0246] Modifications (ranging from first through fourteenth
modifications) of the above exemplary embodiment will be described
below with reference to FIGS. 17 through 41B.
[0247] Structural components of the modifications, which are
identical to those shown in FIGS. 1 through 16, are denoted by
identical reference characters, and such features will not be
described in detail below. Further, in FIGS. 17 through 41B, the
network 36 and the medical organization 40 are omitted from
illustration.
[First Modification]
[0248] As shown in FIG. 17, a radiographic image capturing
apparatus 10A and a radiographic image capturing system 11A
according to a first modification differ from the exemplary
embodiment shown in FIGS. 1 through 16, in that signals are sent
and received between the portable information terminal 34, the
radiation source device 16, and the cassette device 22 by way of
wireless communications.
[0249] In this case, since the portable information terminal 34,
the radiation source device 16, and the cassette device 22 are
connected wirelessly over the same link (communications link), USB
cables for sending and receiving signals are unnecessary. Owing
thereto, no obstacles are presented that impede the work of the
operator 32. Accordingly, the operator 32 can carry out work with
increased efficiency. Further, by rendering the USB cables
unnecessary, the number of parts of the radiographic image
capturing apparatus 10A are reduced, and assembly of the apparatus
at the site is facilitated.
[0250] As noted above, since the portable information terminal 34,
the radiation source device 16, and the cassette device 22 exist
within the same communications link, transmission and reception of
signals for the camera images, radiographic images, etc., to and
from the communication unit 104 (see FIGS. 1 and 11) of the medical
organization 40 can be performed via any one of the communication
units 136, 170, 218 (see FIG. 10).
[0251] Apart from transmission and reception of signals between the
portable information terminal 34, the radiation source device 16,
and the cassette device 22 being carried out by way of wireless
communications, the first modification is the same as the exemplary
embodiment of FIGS. 1 through 16. Therefore, the various effects
and advantages apart from those pertaining to transmission and
reception of signals can easily be obtained. Further, with the
first modification, instead of the aforementioned wireless
communications, signals may be sent and received by way of optical
wireless communications using infrared radiation or the like.
[Second Modification]
[0252] A radiographic image capturing apparatus 10B and a
radiographic image capturing system 11B according to a second
modification differ from the exemplary embodiments shown in FIGS. 1
through 17, in that, as shown in FIG. 18, the web camera 30 is
accommodated in the radiation source device 16, and the web camera
30 captures an image of the guide lines 46 as the image capturing
region 28.
[0253] Accordingly, with the second modification, the web camera 30
and the radiation source device 16 are constructed integrally. In
this case, integral construction of the web camera 30 and the
radiation source device 16 is not limited to the structure shown in
FIG. 18, in which the web camera 30 is incorporated in the
radiation source device 16, but may also include a configuration in
which the web camera 30 and the radiation source device 16 are
joined together (connected) integrally at least at times that the
radiographic image capturing apparatus 10B is being used.
[0254] More specifically, the web camera 30 may be made integral
with the radiation source device 16 in any of the following
configurations (1) through (3). (1) The web camera 30 is connected
electrically to the radiation source device 16 by a cable, which is
included in the radiographic image capturing apparatus 10B. (2) The
web camera 30 is connected to the radiation source device 16 by a
cable, which is provided by the operator 32. (3) During times that
the radiographic image capturing apparatus 10B is in use, the
radiation source device 16 is coupled to the web camera 30, and at
times that the radiographic image capturing apparatus 10B is
serviced for maintenance or is not in use, the web camera 30 can be
spaced (or separated) from the radiation source device 16.
[0255] In configuration (3) as well, in order to enable the web
camera 30 to be spaced from the radiation source device 16 at times
that the radiographic image capturing apparatus 10B is serviced for
maintenance or is not in use, the web camera 30 may be coupled to
the radiation source device 16 by a coupling means such as a clip
or the like. Owing thereto, the web camera 30 is coupled to the
radiation source device 16 by the coupling means only at times that
the radiographic image capturing apparatus 10 is in use. Further,
the coupling means may be equipped with a ball joint to allow the
web camera 30, which is coupled to the radiation source device 16,
to freely change the orientation thereof. If the web camera 30 is
coupled to the radiation source device 16 by the coupling means, it
is a matter of course that the web camera 30 and the radiation
source device 16 must be connected to each other through a wired
link (e.g., a USB cable) or a wireless link.
[0256] Furthermore, if the web camera 30 and the radiation source
device 16 are connected to each other through a cable, then since
the web camera 30 can be placed independently in any desired
position, the web camera 30 can be positioned with greater freedom
than if the web camera 30 were incorporated in the radiation source
device 16.
[0257] Further, in the second modification, only the location of
the guide lines 46 is displayed in the camera image of the web
camera 30, and therefore, in the case that the camera image is sent
to the portable information terminal 34 from the web camera 30 via
the USB cable 24, and the camera image is displayed on the display
unit 64 of the portable information terminal 34, the doctor 38 can
easily determine whether or not the region to be imaged of the
subject 18 is included within the outer frame of the guide lines
46.
[0258] Apart from the web camera 30 being incorporated in the
radiation source device 16, the second modification is the same as
the exemplary embodiment of FIGS. 1 through 16, and therefore, the
various effects and advantages of FIGS. 1 through 16, apart from
those pertaining to incorporation of the web camera 30 in the
radiation source device 16, can easily be obtained.
[Third Modification]
[0259] A radiographic image capturing apparatus 10C and a
radiographic image capturing system 11C according to a third
modification differ from the exemplary embodiments shown in FIGS. 1
through 18, in that, as shown in FIG. 19, a separate web camera 30
is connected electrically and joined integrally with the portable
information terminal 34 by a USB cable 240 having connectors 242,
244.
[0260] In this case, the web camera 30 is supplied with electric
power from the battery 220 through the USB cable 240, whereas the
camera image is sent to the portable information terminal 34 via
the USB cable 240. Accordingly, by integrally constructing the
separate web camera 30 and the portable information terminal 34 in
this manner, although the number of parts of the radiographic image
capturing apparatus 10C increases, the advantages of the apparatus
shown in FIGS. 1 through 16 can easily be obtained. Further,
because the web camera 30 can be arranged independently at any
desired position within the range allowed by the length of the USB
cable 240, in comparison to a structure in which the web camera 30
is incorporated in the portable information terminal 34, the degree
of freedom in positioning the web camera 30 can be increased. In
FIG. 19, the communication unit 260 is shown as being mounted on
the web camera 30. In this case, with the communication unit 260,
transmission and reception of signals such as radiographic images
and camera images, etc., may be carried out directly between the
communication unit 260 and the communication unit 104 of the
medical organization 40 via the network 36 (see FIGS. 1 and
10).
[Fourth Modification]
[0261] A radiographic image capturing apparatus 10D and a
radiographic image capturing system 11D according to a fourth
modification differ from the exemplary embodiment shown in FIGS. 1
through 16, in that, as shown in FIG. 20, a web camera 246 also is
provided in the lid 66 for capturing an image of the operator 32
during times that the portable information terminal 34 is
operated.
[0262] In this case, the portable information terminal 34 transmits
to the medical organization (see FIGS. 1 and 11) the camera image
from the web camera 246 (i.e., the image of the operator 32) by way
of wireless communications over the network 36. Therefore, the
operator 32 can seek instructions concerning capturing of images
while observing the image of the doctor 38 displayed on the display
unit 64, whereas the doctor 38 can issue instructions to the
operator 32 while observing the image of the operator 32 displayed
on the display unit 112. Accordingly, the operator 32 can feel a
sense of proximity to the doctor 38 who is in a remote location
such as the medical organization 40, whereas the doctor 38 can feel
a sense of proximity to the operator 32 who is at the site, and
thus the operator 32 and the doctor 38 can carry out image
capturing preparations with increased confidence and security.
[0263] Further, because in other aspects, apart from the advantages
that come about from providing the web camera 246, the fourth
modification is the same as the exemplary embodiment of FIGS. 1
through 16, the various effects and advantages thereof can easily
be obtained.
[Fifth Modification]
[0264] As shown in FIG. 21, a radiographic image capturing
apparatus 10E and a radiographic image capturing system 11E
according to a fifth modification differ from the exemplary
embodiments shown in FIGS. 1 through 20, in that the radiation
source device 16 is made integral with the lid 66 as a result of
being joined thereto.
[0265] In this case, since the USB cable 24 is unnecessary, the
radiographic image capturing apparatus 10E can be assembled and
accommodated more easily at the site. Further, since the radiation
source device 16 and the portable information terminal 34 are made
integral with each other, the battery 134, the communication unit
136, and the radiation source controller 138 may be dispensed with.
More specifically, the battery 220 is shared as a battery of the
radiation source device 16, the control processor 222 is shared as
a radiation source controller of the radiation source device 16,
and the communication unit 218 is shared as a communication unit of
the radiation source device 16. Thus, the radiation source device
16 is simplified in structure, thereby enabling the radiographic
image capturing apparatus 10E to be made smaller in size as a
whole.
[0266] Moreover, since the radiation source device 16 and the
portable information terminal 34 are made integral with each other,
the operator 32 can change the position and orientation of the
portable information terminal 34 while viewing the display unit 64
or while operating the operating unit 60, thereby simultaneously
adjusting the position and orientation of the radiation source
device 16 with respect to the cassette device 22 and the subject
18. According to the fifth modification, therefore, the position
and orientation of the radiation source device 16 with respect to
the cassette device 22 and the subject 18 can be adjusted
easily.
[0267] In FIG. 21, the web camera 30 is incorporated in the lid 66.
However, the web camera 30 may also be incorporated in the
radiation source device 16. Further, since the fifth modification
is the same as the exemplary embodiments shown in FIGS. 1 through
20, apart from the fact that the radiation source device 16 and the
portable information terminal 34 are made integral with each other,
the fifth modification offers the same advantages as the exemplary
embodiments shown in FIGS. 1 through 20, except that the radiation
source device 16 and the portable information terminal 34 are made
integral with each other.
[Sixth Modification]
[0268] As shown in FIG. 22, a radiographic image capturing
apparatus 10F and a radiographic image capturing system 11F
according to a sixth modification differ from the exemplary
embodiments shown in FIGS. 1 through 21, in that the radiation
source 14 comprises a conventional thermionic-emission radiation
source, and the radiographic image capturing apparatus 10F includes
a high-voltage power supply 252 for energizing a filament of the
radiation source 14.
[0269] In this case, the radiation source 14 and the communication
unit 136 are housed in a casing 250, which is mounted on the upper
end of a stand 248, and the casing 250 is electrically connected to
the high-voltage power supply 252 by the USB cable 24. Further, the
high-voltage power supply 252 and the portable information terminal
34 are electrically connected to each other by a USB cable 254
having connectors 256 and 258. Accordingly, the portable
information terminal 34 can control the high-voltage power supply
252 to cause the radiation source 14 to emit radiation 12.
[0270] According to the sixth modification, the radiographic image
capturing apparatus 10F is relatively large in size and has a
relatively large number of parts, because the radiographic image
capturing apparatus 10F includes a conventional thermionic-emission
radiation source. However, the sixth modification offers the same
advantages as those of the exemplary embodiment shown in FIGS. 1
through 16, except that the radiation source 14 is a
thermionic-emission type of radiation source.
[0271] As shown in FIG. 22, the high-voltage power supply 252
includes a communication unit 262, which is capable of sending and
receiving signals representing radiographic images, camera images,
etc., to and from the communication unit 104 of the medical
organization 40 via the network 36 (see FIGS. 1 and 10).
[Seventh Modification]
[0272] As shown in FIG. 23, a radiographic image capturing
apparatus 10G and a radiographic image capturing system 11G
according to a seventh modification differ from the exemplary
embodiments shown in FIGS. 1 through 22, in that the portable
information terminal 34 is not provided, but rather, the
radiographic image capturing apparatus 10G is constituted by a
separate web camera 30, the radiation source device 16, and the
cassette device 22, and transmission and reception of signals
therebetween is carried out by way of wireless communications.
[0273] In this case, since the radiation source device 16, the
cassette device 22, and the web camera 30 are connected wirelessly
over a common communications link, transmission and reception of
signals including camera images, radiographic images, etc., with
the communication unit 104 (see FIGS. 1 and 11) of the medical
organization 40 may be performed through any one of the
communication units from among the communication unit 260 of the
web camera 30 and the communication units 136, 170 (see FIG. 10).
For example, the web camera 30 may transmit camera images directly
to the medical organization 40 from the communication unit 260 over
the network 36 (see FIGS. 1 and 10), or alternatively, the camera
images may be transmitted indirectly from the communication unit
260 to the medical organization 40 by way of the communication unit
170 of the cassette device 22, or by way of the communication unit
136 of the radiation source device 16.
[0274] Further, because the web camera 30 is arranged
independently, the web camera 30 can be disposed in any desired
position, and accordingly, the degree of freedom in positioning the
web camera 30 can be enhanced.
[0275] Moreover, in the seventh modification, a synchronization
control signal may be generated by the radiation source controller
138 of the radiation source device 16 or by the cassette controller
168 of the cassette device 22, or alternatively, may be supplied
from the console 106 via the communication unit 104, the antenna
102, and the network 36.
[0276] In this case as well, the doctor 38 is able to observe the
camera image from the web camera 30. Further, by providing the
speaker 78 and the microphone 80 in the web camera 30, the
radiation source device 16, or the cassette device 22, the operator
32 can seek instructions and advice pertaining to image capturing
from the doctor 38, and such instructions can be given to the
operator 32 from the doctor 38. More specifically, in the seventh
modification, because the display unit 64 is not provided, image
capturing preparations according to instructions from the doctor 38
are carried out by way of the operator 32 listening to voice
messages of the doctor 38 from the speaker 78.
[0277] Apart from the portable information terminal 34 not being
provided, and the fact that transmission and reception of signals
between the web camera 30, the radiation source device 16 and the
cassette device 22 are carried out by way of wireless
communications, the seventh modification is essentially the same as
the exemplary embodiment of FIGS. 1 through 16, and therefore,
aside from the advantages that come about due to the absence of the
portable information terminal 34 and by wireless transmission and
reception of signals, the same advantages and effects of the
exemplary embodiment of FIGS. 1 through 16 can be obtained.
[Eighth Modification]
[0278] As shown in FIG. 24, a radiographic image capturing
apparatus 10H and a radiographic image capturing system 11H
according to an eighth modification differ from the seventh
embodiment shown in FIG. 23, in that the web camera 30 is
incorporated in the radiation source device 16.
[0279] In this case, similar to the second modification shown in
FIG. 18, the web camera 30 captures an image of the guide lines 46
as the image capturing region 28.
[0280] Further, with the eighth modification, since the radiation
source device 16 and the cassette device 22 are connected
wirelessly over a common communications link, transmission and
reception of signals including camera images, radiographic images,
etc., with the communication unit 104 (see FIGS. 1 and 11) of the
medical organization 40 may be performed through any one of the
communication units from among the communication units 136, 170
(see FIG. 10). For example, the web camera 30 may transmit camera
images directly to the medical organization 40 from the
communication unit 136 over the network 36, or alternatively, the
camera images may be transmitted indirectly from the communication
unit 136 to the medical organization 40 by way of the communication
unit 170 of the cassette device 22.
[0281] Furthermore, with the eighth modification, by incorporating
the web camera 30 internally in the radiation source device 16, the
number of parts can be further reduced. Apart from the web camera
30 being incorporated in the radiation source device 16, the eighth
modification is essentially the same as the seventh modification
shown in FIG. 23, and therefore, aside from the advantages that
come about by constructing the web camera 30 integrally with the
radiation source device 16, the same advantages and effects of the
seventh modification of FIG. 23 can be obtained.
[Ninth Modification]
[0282] As shown in FIG. 25, a radiographic image capturing
apparatus 10I and a radiographic image capturing system 11I
according to a ninth modification differ from the exemplary
embodiments shown in FIGS. 1 through 24, in that the console 106
and a plurality of attache cases 98, each of which houses therein
the radiographic image capturing apparatus 10I, are provided in a
medical checkup car 300 (waiting location) in which the doctor 38
is available, and the operator 32 (see FIG. 5) carries at least one
of the attache cases 98 from the medical checkup car 300 to the
site. The cabin of the medical checkup car 300 where the doctor 38
is available serves as a waiting location from which the doctor 38
is unable to observe the subject 18 directly.
[0283] In this case as well, the radiographic image capturing
apparatus 10I, which has been carried to the site, and the
communication unit 104 in the medical checkup car 300 are capable
of sending and receiving signals therebetween by way of wireless
communications. For example, the radiographic image capturing
apparatus 10I can send wireless signals representing camera images
and radiographic images to the communication unit 104 by way of
wireless communications. Therefore, the radiographic image
capturing apparatus 10I offers the same advantages as the exemplary
embodiments shown in FIGS. 1 through 24. Although the radiographic
image capturing apparatus 10I and the communication unit 104 are
illustrated in FIG. 25 as sending and receiving signals directly
therebetween by way of wireless communications, the radiographic
image capturing apparatus 10I and the communication unit 104 may
also send and receive signals therebetween by way of wireless
communications via the network 36 (see FIGS. 1 and 10).
[Tenth Modification]
[0284] As shown schematically in FIGS. 26A through 30B, a
radiographic image capturing apparatus 10J and a radiographic image
capturing system 11J according to a tenth modification differ from
the exemplary embodiments shown in FIGS. 1 through 25, in that
radiation 12a to 12c with an irradiation range narrower than that
of the radiation 12 (see FIG. 1) is irradiated through the subject
18 simultaneously or sequentially from the radiation source device
16 to the cassette device 22.
[0285] In the tenth modification, with respect to radiation applied
at the disaster site or the home care treatment site, the radiation
intensity thereof is set to be weak for the purpose of safety
(i.e., to prevent unnecessary or accidental exposure to radiation).
In addition, image capturing of the subject 18 is performed
effectively by the radiation 12a to 12c within a narrow irradiation
range, which is narrower than that of the radiation 12, in a
condition in which the radiation source device 16 is placed in
close proximity to the cassette device 22 with a short SID (source
to image distance).
[0286] Initially, in the case of FIGS. 26A and 26B, a plurality of
radiation sources 14a to 14c are accommodated at predetermined
distances in the interior of the radiation source device 16, and
after irradiation light 54 is output from the irradiated field lamp
56 and projected onto the irradiated surface 44 (see FIGS. 1, 7 and
16), radiation 12a to 12c is applied simultaneously to (the
irradiated surface 44 of) the cassette device 22 from each of the
radiation sources 14a to 14c. In this case, radiation 12a to 12c
from each of the radiation sources 14a to 14c is output
collectively such that a portion of the radiation 12a and a portion
of the radiation 12b, and also a portion of the radiation 12b and a
portion of the radiation 12c overlap one another. Consequently,
each of such radiations 12a to 12c can be applied reliably and
without gaps with respect to the total region within the outer
frame of the guide lines 46. As a result, even though the radiation
intensity is set to be weak, image capturing of the subject 18 can
be carried out reliably.
[0287] In the case of FIGS. 27A to 28B, inside the radiation source
device 16, a rail 302 is disposed along a longitudinal direction of
the radiation source device 16, and the radiation source 14 is
constituted so as to be movable along the rail 302. In this case,
after irradiation light 54 is output from the irradiated field lamp
56 and projected onto the irradiated surface 44 (see FIGS. 1, 7,
and 16), the radiation source 14 moves along the rail 302, and
radiation 12a to 12c is applied repeatedly at predetermined
positions after movement thereof. At this time, the radiation
source 14 is moved, and radiation 12a to 12c from the radiation
source 14 is output at the positions shown in FIGS. 27B, 28A, and
28B, such that a portion of the radiation 12a and a portion of the
radiation 12b, and also a portion of the radiation 12b and a
portion of the radiation 12c overlap one another. In this case as
well, since each of such radiations 12a to 12c can be applied
reliably and without gaps with respect to the total region within
the outer frame of the guide lines 46, even though the radiation
intensity is set to be weak, image capturing of the subject 18 can
be carried out reliably.
[0288] In the case of FIGS. 29A through 30B, after irradiation
light 54 is output from the irradiated field lamp 56 and projected
onto the irradiated surface 44 (see FIGS. 1, 7 and 16), the
radiation source 14 is rotated by a non-illustrated rotation
mechanism, and after rotation thereof, radiation 12a to 12c is
applied repeatedly at respective predetermined angles. At this
time, the radiation source 14 is rotated to the angles shown in
FIGS. 29B, 30A, and 30B, and radiation 12a to 12c is output such
that a portion of the radiation 12a and a portion of the radiation
12b, and also a portion of the radiation 12b and a portion of the
radiation 12c overlap one another. In this case as well, since each
of such radiations 12a to 12c can be applied reliably and without
gaps with respect to the total region within the outer frame of the
guide lines 46, even though the radiation intensity is set to be
weak, image capturing of the subject 18 can be carried out
reliably.
[0289] Further, according to the tenth modification, in the
radiographic image obtained from the radiation 12a to 12c, at the
location where the radiation 12a and the radiation 12b overlap, and
at the location where the radiation 12b and the radiation 12c
overlap, a known type of corrective process, such as shading
correction or the like, may be implemented thereon.
[0290] Further, in the examples of FIGS. 27A to 30B, since each of
such radiations 12a to 12c may be applied reliably and without gaps
with respect to the total region within the outer frame of the
guide lines 46, it is acceptable if at least two of such radiation
sources 14a to 14c are provided. On the other hand, the sequence of
movement or rotation of the radiation source 14, the positions
thereof after movement, or the angles thereof after rotation are
not limited to the sequence, positions, and angles shown in FIGS.
27B to 28B and 29B to 30B, and the sequence, positions, and angles
thereof may be set in other suitable ways.
[0291] Further, in the tenth modification, aside from the radiation
12a to 12c being applied simultaneously or sequentially, in other
respects the tenth modification is the same as the exemplary
embodiments of FIGS. 1 through 25, and therefore, aside from
radiating the subject 18 with respective radiations 12a to 12c, the
tenth modification offers the same advantages as the exemplary
embodiments shown in FIGS. 1 through 25.
[0292] FIGS. 31A to 33B illustrate a case in which positioning of
the subject 18 is carried out using the web camera 30, which is
incorporated in the radiation source device 16, and a case in which
positional shifting or slippage of the radiation source device 16
is detected based on the camera image captured by the web camera
30, in the second and eighth modifications.
[0293] As shown in FIG. 31A, in the case that a horizontal axis 304
passing through the center of the web camera 30 and the central
position of the guide lines 46 are substantially perpendicular,
then as shown in FIG. 31B, the region to be imaged of the subject
18 and the cassette device 22 are displayed in the center of the
camera image displayed on the display unit 64 of the portable
information terminal 34 (see FIGS. 1 and 10), or on the display
unit 112 of the console 106 (see FIGS. 1 and 11). Further, in FIG.
31B, the cross hairs in the camera image indicate a center position
of the camera image, and assuming the horizontal axis 304 and the
center position of the guide lines 46 are substantially
perpendicular, the cross hairs and the center position of the guide
lines 46 coincide with each other.
[0294] Accordingly, during image capturing preparations, while the
operator 32 observes the camera image, by instructing the subject
18, or by adjusting the position of the radiation source device 16
such that the cross hairs coincide with the center position of the
guide lines 46, even without visually confirming the subject 18
directly, positioning of the subject 18 can easily be carried out.
Moreover, in the case of FIG. 31B, similar to the case of FIGS. 14A
and 14B, by bringing the cross hairs and the center position of the
guide lines 46 into substantial agreement with each other, the
characters "POSITIONING IS OK" are displayed to indicate that image
capturing preparations have been completed.
[0295] In addition, if image capturing is carried out in the
condition shown in FIGS. 31A and 31B, then as shown in FIG. 33A, a
radiographic image of a desired imaging region can reliably be
obtained. FIG. 33A shows the content displayed on the display units
64, 112 following completion of image capturing, in which the
radiographic image of the region to be imaged of the subject 18 is
displayed in a large size. Together therewith, similar to the case
of FIGS. 15A and 15B, a camera image of the subject 18 and the
cassette device 22 after image capturing is displayed in a smaller
size along with displaying the characters "IMAGE CAPTURING IS
COMPLETED" for indicating that the image-capturing has been
completed. Further, since following image capturing, it is
desirable for the doctor to rapidly carry out radiographic image
diagnosis, by displaying the radiographic image in a larger size
than the other displayed content, radiographic image diagnosis can
be performed quickly and effectively.
[0296] In contrast thereto, as shown in FIG. 32A, if the horizontal
axis 304 and the center position of the guide lines 46 are not
perpendicular and are significantly separated, then as shown in
FIG. 32B, the cross hairs in the camera image and the center
position of the guide lines 46 do not coincide with each other.
Thus, the operator 32 can easily grasp that positional shifting of
the radiation source device 16 with respect to the cassette device
22 has occurred.
[0297] Accordingly, while observing the camera image while image
capturing preparations are carried out, the operator 32 can adjust
the position of the radiation source device 16 so as to bring the
cross hairs and the center position of the guide lines 46 into
substantial agreement (i.e., so that the display content of FIG.
31B appears). Further, the operator 32 can reliably be notified of
any positional shifting of the radiation source device 16 with
respect to the cassette device 22. Further, similar to the case of
FIG. 14C, as shown in FIG. 32B, at times that positional shifting
of the radiation source device 16 with respect to the cassette
device 22 occurs, the characters "MOVE/REPOSITION RADIATION SOURCE
TO CENTER OF CASSETTE" are displayed to instruct the operator 32 to
carry out image capturing preparations once again.
[0298] Incidentally, in the event that image capturing is carried
out irrespective of the content displayed in FIG. 32B, or if
shifting of the radiation source device 16 occurs during image
capturing, then as shown in FIG. 33B, a radiographic image for
which capturing was a failure is displayed together with the camera
image of the subject 18 and the cassette device 22 after image
capturing, and similar to the case of FIG. 15C, the characters
"IMAGE CAPTURING IS NO GOOD, PLEASE REPEAT IMAGE CAPTURING" are
displayed respectively on the display units 64, 112, for indicating
image-recapturing. Accordingly, by confirming the displayed
content, the operator 32 can easily comprehend that image capturing
was a failure, and that recapturing of the image is necessary.
[0299] In the foregoing manner, in the case of FIGS. 31A through
33B, positioning of the subject 18 is carried out using the web
camera 30 that is incorporated in the radiation source device 16,
and together therewith, based on the camera image capturing by the
web camera 30, positional shifting of the radiation source device
16 is detected. Owing thereto, during image capturing preparations,
the operator 32 can reliably be notified of any positional shifting
or slippage, so that image capturing preparations can be carried
out effectively, together with enabling a desired radiographic
image to be obtained reliably. Further, if by chance, even in the
case that image capturing is a failure, a notification can reliably
be given to repeat image capturing, thus enabling image recapturing
to be performed swiftly.
[Eleventh Modification]
[0300] As shown in FIGS. 34 through 37B, a radiographic image
capturing apparatus 10K and a radiographic image capturing system
11K according to an eleventh modification differ from the exemplary
embodiments shown in FIGS. 1 through 33B, in that the radiation
source device 16 includes a handle 310 to be gripped by the
operator 32, which is disposed on a side of the radiation source
device 16 opposite from a location thereof on which radiation 12 is
output.
[0301] In this case, while the operator 32 grips the handle 310
with one hand, the radiation source device 16 incorporating the web
camera 30 therein is directed toward the subject 18 and the
cassette device 22. At the same time, the operator 32 can operate
the portable information terminal 34 with the other hand while
observing the display unit 64. At this time, the camera image
captured by the web camera 30 is displayed on the display unit 64,
and therefore, the operator 32 can carry out positioning of the
subject 18 while observing the camera image and moving the
radiation source device 16 to a desired position. Further, even in
the case that radiation 12 is emitted while the operator 32 grips
the handle 310, application of radiation 12 toward the operator 32
(exposure of the operator 32) can reliably be avoided.
[0302] The eleventh modification is particularly applicable and
effective at disaster sites where several obstacles may be present.
More specifically, at such disaster sites, since there are many
obstacles, and it may be difficult to move the subject 18 due to
injury of the subject 18 at the disaster site, as a practical
matter, it is difficult to secure the radiation source device 16
and the cassette device 22 at given positions and to guide the
subject 18 to a position between the radiation source device 16 and
the cassette device 22. Accordingly, the radiation source device 16
and the cassette device 22 frequently need to be located at
positions that are convenient to the subject 18. For this reason,
although the operator 32 can direct the radiation source device 16
toward the subject 18, it may be difficult to observe the subject
18 directly due to the presence of obstacles. Consequently, it may
not be easy to position the subject 18.
[0303] Thus, according to the eleventh modification, if the
operator 32 grips the handle 310 with one hand and directs the
radiation source device 16 toward the subject 18 and the cassette
device 22, the web camera 30 captures a camera image of the subject
18 and the cassette device 22, and the captured camera image is
displayed on the display unit 64. Accordingly, the operator 32 can
easily operate the portable information terminal 34 with the other
hand, or adjust the position of the radiation source device 16 and
position the subject 18, while viewing the camera image displayed
on the display unit 64.
[0304] The handle 310 includes an electrostatic capacitance or
resistance film type of touch sensor (gripping state detecting
sensor) 312 (see FIGS. 35 through 36B). If the operator 32 grips
the handle 310, the hand of the operator 32 comes into contact with
a non-illustrated electrode constituting the touch sensor 312,
whereupon, the touch sensor 312 outputs a detection signal to the
radiation source controller 138 and the control processor 222 (see
FIG. 10) based on contact between the operator's hand and the
electrode. The radiation source controller 138 or the control
processor 222 is able to activate the radiation source device 16 or
operate the cassette device 22 based on the aforementioned
detection signal.
[0305] Further, as shown in FIGS. 37A and 37B, the radiation source
device 16 may include a recess 324 defined in a side opposite from
the location where radiation 12 is emitted, and a collapsible
handle 320 may be disposed in the recess 324. A touch sensor 322,
which has the same function as the touch sensor 312, may be
incorporated in the handle 320. In a state in which the operator 32
is not carrying the radiation source device 16, the handle 320 is
accommodated inside the recess 324 as shown in FIG. 37A. On the
other hand, if the operator 32 turns the handle 320 about a
proximal end, the handle 320 is raised out of the recess 324, so
that the operator 32 can grip the handle 320. In this case as well,
the handle 320 and the touch sensor 322 offer the same advantages
as those of the handle 310 and the touch sensor 312 described
above.
[0306] Further, in a case where the handle 320 is accommodated in
the recess 324 (e.g., in a case where the radiation source device
16 is moved as shown in FIGS. 5 and 37A), the electrode of the
touch sensor 322 is kept out of contact with the hand of the
operator 32. Therefore, during activation of the radiation source
device 16, the radiation source 14 can be prevented from emitting
radiation 12 in error.
[0307] Apart from the features of the handles 310, 320 being
provided on the radiation source device 16, the eleventh
modification is the same as the exemplary embodiments shown in
FIGS. 1 through 33B, and therefore, aside from the advantages that
are brought about due to providing the handles 310, 320, the same
effects and advantages of the embodiments of FIGS. 1 through 33B
can easily be obtained.
[Twelfth Modification]
[0308] As shown in FIG. 38, a radiographic image capturing
apparatus 10L and a radiographic image capturing system 11L
according to a twelfth modification differ from the eleventh
modification (see FIGS. 34 to 37B), in that the web camera 30 is
incorporated in the portable information terminal 34, and the
portable information terminal 34 is constructed integrally with the
web camera 30.
[0309] In this case, the web camera 30 captures an image of the
radiation source device 16, the subject 18, and the cassette device
22, and the portable information terminal 34 displays the captured
camera image on the display unit 64. Accordingly, with the twelfth
modification as well, the same advantages as those of the eleventh
modification can be obtained.
[0310] Further, with the twelfth modification, as shown in FIG. 39,
a separate web camera 30 may be connected electrically with the
portable information terminal 34 via a USB cable 240, whereby the
web camera 30 and the portable information terminal are connected
integrally in this manner. Even in this case, since the web camera
30 captures an image of the radiation source device 16, the subject
18, and the cassette device 22, and transmits the camera image to
the portable information terminal 34 by way of the USB cable 240,
the same advantages as those of the modification shown in FIG. 38
can be obtained. Further, similar to the case of the third
modification (see FIG. 19), the web camera 30 can be arranged
independently at any desired position within the range allowed by
the length of the USB cable 240, and therefore, in this case as
well, the degree of freedom in positioning the web camera 30 can be
enhanced.
[Thirteenth Modification]
[0311] As shown in FIG. 40, a radiographic image capturing
apparatus 10M and a radiographic image capturing system 11M
according to a thirteenth modification differ from the eleventh
modification (see FIGS. 34 to 37B) and the twelfth modification
(see FIGS. 38 and 39), in that a separate web camera 30 is
connected electrically to the radiation source device 16 via a USB
cable 240, and the web camera 30 and the radiation source device 16
are connected together integrally in this manner.
[0312] In this case, the web camera 30 captures an image of the
radiation source device 16, the subject 18, and the cassette device
22, transmits a camera image to the radiation source device 16 via
the USB cable 240, and the radiation source device 16 transfers the
camera image to the portable information terminal 34 by way of
wireless communications. Accordingly, the portable information
terminal 34 displays the transferred camera image on the display
unit 64. Thus, even in the case of the thirteenth modification, the
same effects and advantages as those of the eleventh modification
and the twelfth modification can be obtained. Further, as in the
third modification (see FIG. 19) and the twelfth modification (see
FIG. 39), because the web camera 30 can be arranged independently
at any desired position within the range allowed by the length of
the USB cable 240, the degree of freedom in positioning the web
camera 30 can be increased also in this case.
[0313] Incidentally, in the thirteenth modification, a camera image
may be transmitted directly to the portable information terminal 34
from the web camera 30 by use of wireless communications.
[Fourteenth Modification]
[0314] In each of the radiographic image capturing apparatus 10,
10A through 10M (radiographic image capturing systems 11, 11A
through 11M), the radiation detector 20 may be constructed as shown
in FIGS. 41A and 41B (fourteenth modification). According to the
fourteenth modification, a specific structure of the radiation
detector, which comprises a scintillator of CsI, will be described
in detail below.
[0315] According to the fourteenth modification shown in FIGS. 41A
and 41B, the radiation detector 20 includes a scintillator 500 for
converting radiation 12 that has passed through the subject 18 (see
FIGS. 1 through 4, 10, 17 through 31A, 32A, 34, 36A, 36B, and 38
through 40) into visible light (absorbing radiation 12 and emitting
visible light), and a radiation detector 502 for converting visible
light generated by the scintillator 500 into electric signals
(electric charges) depending on a radiographic image. In FIGS. 41A
and 41B, the grid 162 and the lead plate 164 (see FIGS. 3, 4, 7,
31A, 32A, 36A and 36B) are omitted from illustration.
[0316] As shown in FIGS. 41A and 41B, the radiation detector 20 may
be a face-side readout type, i.e., and ISS (Irradiation Side
Sampling) type, which includes the radiation detector 502 and the
scintillator 500 arranged successively with respect to the
irradiated surface 44 that is irradiated with radiation 12, or a
reverse-readout type, i.e., a PSS (Penetration Side Sampling) type,
which includes the scintillator 500 and the radiation detector 502
arranged successively with respect to the irradiated surface
44.
[0317] The scintillator 500 emits stronger light from the
irradiated surface 44, which is irradiated with radiation 12.
According to an ISS type, the light emission position of the
scintillator 500 is closer to the radiation detector 502.
Therefore, the ISS type allows the captured radiographic image to
exhibit higher resolution, while also allowing the radiation
detector 502 to detect a greater amount of visible light than a PSS
type. The ISS type is thus effective to increase the sensitivity of
the radiation detector 20 (cassette device 22) higher than that of
a PSS type.
[0318] The scintillator 500 may be made of a material such as
CsI:Tl (cesium iodide with added thallium), CsI:Na
(sodium-activated cesium iodide), GOS (Gd.sub.2O.sub.2S:Tb), or the
like.
[0319] FIG. 41B shows by way of example a scintillator 500, which
includes a columnar crystalline region formed by evaporating a
material containing CsI on an evaporated substrate 504.
[0320] More specifically, the scintillator 500 shown in FIG. 41B
includes a columnar crystalline region of columnar crystals 500a
near the irradiated surface 44 (the radiation detector 502) to
which radiation 12 is applied, and a non-columnar crystalline
region of non-columnar crystals 500b positioned remotely from the
irradiated surface 44. The evaporated substrate 504 preferably is
made of a highly heat resistant material, e.g., aluminum (Al), in
light of its low cost. The columnar crystals 500a have an average
diameter, which is substantially uniform along the longitudinal
directions of the columnar crystals 500a.
[0321] As described above, the scintillator 500 is made up of the
columnar crystalline region (columnar crystals 500a) and the
non-columnar crystalline region (non-columnar crystals 500b), in
which the columnar crystalline region, which comprises columnar
crystals 500a that are capable of emitting light highly
efficiently, is disposed near the radiation detector 502.
Therefore, visible light generated by the scintillator 500 travels
through the columnar crystals 500a and is emitted toward the
radiation detector 502. As a result, visible light emitted toward
the radiation detector 502 is prevented from scattering, which in
turn prevents the radiographic image detected by the cassette
device 22 from becoming blurred. Visible light that has reached a
deeper region (non-columnar crystalline region) of the scintillator
500 is reflected toward the radiation detector 502 by the
non-columnar crystals 500b. Consequently, the amount of visible
light that is applied to the radiation detector 502 (the efficiency
at which visible light emitted by the scintillator 500 is detected)
can be increased.
[0322] If it is assumed that the thickness of the columnar
crystalline region of the scintillator 500, which is positioned
near the irradiated surface 44, is represented by t1, whereas the
thickness of the non-columnar crystalline region of the
scintillator 500, which is positioned near the evaporated substrate
504, is represented by t2, then the thicknesses t1, t2 preferably
satisfy the relationship 0.01.ltoreq.t2/t1.ltoreq.0.25.
[0323] Since the thickness t1 of the columnar crystalline region
and the thickness t2 of the non-columnar crystalline region satisfy
the above relationship, the ratio along thickness-wise directions
of the scintillator 500 between the region (columnar crystalline
region), which has high light emission efficiency to prevent
visible light from being scattered, and the region (non-columnar
crystalline region), which reflects visible light, is in an
appropriate range for increasing light emission efficiency of the
scintillator 500, and the efficiency at which the visible light
emitted by the scintillator 500 is improved, together with
enhancing the resolution of the radiographic image.
[0324] If the thickness t2 of the non-columnar crystalline region
is too large, then a region with low light emission efficiency
increases, resulting in a reduction in sensitivity of the cassette
device 22. Therefore, the ratio (t2/t1) preferably is in a range
from 0.02 to 0.1.
[0325] It has been described above that the scintillator 500
includes the columnar crystalline region and the non-columnar
crystalline region in a continuous array. However, the scintillator
500 may include the columnar crystalline region and a light
reflecting layer of Al or the like, which replaces the non-columnar
crystalline region.
[0326] The radiation detector 502 serves to detect visible light
emitted from the light emission side (columnar crystal 500a) of the
scintillator 500. As shown in FIG. 41A, the radiation detector 502
includes an insulating substrate 508, a TFT layer 510, and
photoelectric transducers 512, which are successively deposited on
the irradiated surface 44 along the direction in which radiation 12
is applied. A planarization layer 514 is disposed in covering
relation to the photoelectric transducers 512 on the bottom surface
of the TFT layer 510.
[0327] Further, the radiation detector 502 is constructed as a TFT
active matrix board (hereinafter referred to as a "TFT board")
having a matrix of pixels 520 as viewed in plan on the insulating
substrate 508. Each of the pixels 520 includes one of the
photoelectric transducers 512, which may comprise a photodiode (PD)
or the like, a storage capacitor 516, and a TFT 518.
[0328] The TFT 518 corresponds to the TFT 188 (see FIG. 9)
described above, and the photoelectric transducer 512 and the
storage capacitor 516 correspond to a pixel 180.
[0329] The photoelectric transducer 512 comprises a lower electrode
512a near the scintillator 500, an upper electrode 512b near the
TFT layer 510, and a photoelectric conversion film 512c disposed
between the lower electrode 512a and the upper electrode 512b. The
photoelectric conversion film 512c absorbs visible light emitted
from the scintillator 500, and generates electric charges depending
on the absorbed visible light.
[0330] The lower electrode 512a preferably is made of an
electrically conductive material, which is transparent at least to
the wavelength of light emitted by the scintillator 500, because
the lower electrode 512a needs to apply visible light emitted by
the scintillator 500 to the photoelectric transducer 512. More
specifically, it is preferable to make the lower electrode 512a of
a transparent conducting oxide (TCO), which is highly permeable to
visible light and has a low resistance value.
[0331] Although the lower electrode 512a may be made of a thin
metal film of Au or the like, preferably, the lower electrode 512a
is made of TCO, because the resistance value of a thin metal film
of Au or the like tends to increase if the thin metal film has a
light transmittance of 90% or higher. For example, the lower
electrode 512a may be made of ITO (Indium Tin Oxide), IZO (Indium
Zinc Oxide), AZO (Aluminum-doped Zinc Oxide), FTO (Fluorine-doped
Tin Oxide), SnO.sub.2, TiO.sub.2, ZnO.sub.2, or the like. However,
most preferably, the lower electrode 512a is made of ITO in light
of processing simplicity, low resistance, and transparency. The
lower electrode 512a may be a single electrode shared by all of the
pixels 520, or may be divided into a plurality of electrodes
assigned to each of the pixels 520 respectively.
[0332] Further, the photoelectric conversion film 512c may be made
of a material that absorbs visible light and generates electric
charges. For example, the photoelectric conversion film 512c may be
made of amorphous silicon (a-Si), or an organic photoelectric
conversion material (OPC). If the photoelectric conversion film
512c is made of amorphous silicon, the photoelectric conversion
film 512c can absorb visible light emitted from the scintillator
500 in a wide wavelength range. However, since a photoelectric
conversion film 512c made of amorphous silicon needs to be
evaporated, heat resistance of the insulating substrate 508 should
be taken into consideration if the insulating substrate 508 is made
of synthetic resin.
[0333] If the photoelectric conversion film 512c is made of a
material including an organic photoelectric conversion material,
then the photoelectric conversion film 512c provides an absorption
spectrum, which exhibits a high absorption rate mainly in the
visible range, and hence does not absorb electromagnetic waves
other than visible light emitted by the scintillator 500.
Therefore, noise produced if radiation 12 such as X-rays,
.gamma.-rays, or the like is absorbed by the photoelectric
conversion film 512c can be minimized.
[0334] The photoelectric conversion film 512c, which is made of an
organic photoelectric conversion material, can be formed by
applying an organic photoelectric conversion material to a target
using a liquid droplet ejection head such as an ink jet head or the
like. Therefore, the target does not need to be heat resistant.
According to the fourteenth modification, the photoelectric
conversion film 512c is made of an organic photoelectric conversion
material.
[0335] The photoelectric conversion film 512c, which is made of an
organic photoelectric conversion material, absorbs almost no
radiation 12. Therefore, in an ISS type of radiation detector 20
having the radiation detector 502 arranged to pass radiation 12
therethrough, attenuation of radiation 12 that has passed through
the radiation detector can be reduced, thereby minimizing a
reduction in sensitivity to radiation 12. Therefore, it is
preferable for the photoelectric conversion film 512c to be made of
an organic photoelectric conversion material, particularly if the
radiation detector 20 is of an ISS type.
[0336] In order for the organic photoelectric conversion material
of the photoelectric conversion film 512c to absorb visible light
emitted by the scintillator 500 most efficiently, the absorption
peak wavelength thereof should preferably be as close as possible
to the light emission peak wavelength of the scintillator 500.
Although the absorption peak wavelength of the organic
photoelectric conversion material and the light emission peak
wavelength of the scintillator 500 ideally are in agreement with
each other, it is possible to sufficiently absorb light emitted by
the scintillator 500 if the difference between the absorption peak
wavelength and the light emission peak wavelength is small enough.
More specifically, the difference between the absorption peak
wavelength of the organic photoelectric conversion material and the
light emission peak wavelength of the scintillator 500 with respect
to the radiation 12 preferably is 10 nm or smaller, and more
preferably, is 5 nm or smaller.
[0337] Organic photoelectric conversion materials that meet the
above requirements include quinacridone-based organic compounds and
phthalocyanine-based organic compounds, for example. Since
quinacridone, for example, has an absorption peak wavelength of 560
nm in the visible range, if quinacridone is used as the organic
photoelectric conversion material and CsI:Tl is used as the
material of the scintillator 500, the difference between the above
peak wavelengths can be reduced to 5 nm or smaller, thus making it
possible to substantially maximize the quantity of electric charges
generated by the photoelectric conversion film 512c.
[0338] The photoelectric conversion film 512c, which is applicable
to the radiation detector 20, will be described in specific detail
below.
[0339] The radiation detector 20 includes an electromagnetic wave
absorption/photoelectric conversion region provided by an organic
layer, including the upper electrode 512b and the lower electrode
512a, and the photoelectric conversion film 512c sandwiched between
the upper electrode 512b and the lower electrode 512a. The organic
layer may be formed by superposition or mixture of an
electromagnetic wave absorption region, a photoelectric conversion
region, an electron transport region, a hole transport region, an
electron blocking region, a hole blocking region, a crystallization
prevention region, an electrode, and an interlayer contact
improving region, etc.
[0340] The organic layer preferably includes an organic p-type
compound or an organic n-type compound. An organic p-type
semiconductor (compound) is a donor organic compound typified
mainly by a hole transport organic compound, and refers to an
organic compound that tends to donate electrons. More specifically,
in a case where two organic materials are placed in contact with
each other, one of the organic materials, which has a lower
ionization potential, is referred to as a donor organic compound.
Any type of organic compound which is capable of donating electrons
can be used as a donor organic compound. An organic n-type
semiconductor (compound) is an acceptor organic compound typified
mainly by an electron transport organic compound, and refers to an
organic compound that tends to accept electrons. More specifically,
in a case where two organic materials are placed in contact with
each other, one of the organic materials, which has a larger
electron affinity, is referred to as an acceptor organic compound.
Any type of organic compound which is capable of accepting
electrons can be used as an acceptor organic compound.
[0341] Materials that can be used as the organic p-type
semiconductor and the organic n-type semiconductor, and
arrangements of the photoelectric conversion film 512c are
disclosed in detail in Japanese Laid-Open Patent Publication No.
2009-032854, and will not be described in detail below.
[0342] The photoelectric transducer 512 of each pixel may include
at least the upper electrode 512b, the lower electrode 512a, and
the photoelectric conversion film 512c. For preventing dark current
from increasing, the photoelectric transducer 512 preferably
includes at least one of an electron blocking film and a hole
blocking film, and more preferably, includes both the electron
blocking film and the hole blocking film.
[0343] The electron blocking film may be disposed between the upper
electrode 512b and the photoelectric conversion film 512c. If a
bias voltage is applied between the upper electrode 512b and the
lower electrode 512a, the electron blocking film can prevent
electrons from being injected from the upper electrode 512b into
the photoelectric conversion film 512c, thereby preventing dark
current from increasing. The electron blocking film may be made of
an organic material that can donate electrons. The electron
blocking film actually is made of a material which is selected
depending on the material of the adjacent electrode and the
material of the adjacent photoelectric conversion film 512c. A
preferable material has an electron affinity (Ea), which is at
least 1.3 eV greater than the work function (Wf) of the material of
the adjacent electrode, and an ionization potential (Ip) equal to
or smaller than the Ip of the material of the adjacent
photoelectric conversion film 512c. Materials that can be used as
an organic material and which are capable of donating electrons are
disclosed in detail in Japanese Laid-Open Patent Publication No.
2009-032854, and such materials will not be described in detail
below.
[0344] The thickness of the electron blocking film preferably is in
the range from 10 nm to 200 nm, more preferably, is in the range
from 30 nm to 150 nm, and particularly preferably, is in the range
from 50 nm to 100 nm, in order to reliably achieve a dark current
reducing capability and to prevent the photoelectric conversion
efficiency of the photoelectric transducer 512 from being
lowered.
[0345] The hole blocking film may be disposed between the
photoelectric conversion film 512c and the lower electrode 512a. In
the case that a bias voltage is applied between the upper electrode
512b and the lower electrode 512a, the hole blocking film can
prevent holes from being injected from the lower electrode 512a
into the photoelectric conversion film 512c, thereby preventing
dark current from increasing. The hole blocking film may be made of
an organic material capable of accepting electrons. The hole
blocking film actually is made of a material, which is selected
depending on the material of the adjacent electrode and the
material of the adjacent photoelectric conversion film 512c. A
preferable material should have an ionization potential (Ip), which
is at least 1.3 eV greater than the work function (Wf) of the
material of the adjacent electrode, and an electron affinity (Ea),
which is equal to or greater than the Ea of the material of the
adjacent photoelectric conversion film 512c. Materials that can be
used as an organic material and which can accept electrons are
disclosed in detail in Japanese Laid-Open Patent Publication No.
2009-032854, and such materials will not be described in detail
below.
[0346] The thickness of the hole blocking film preferably is in the
range from 10 nm to 200 nm, more preferably, is in the range from
30 nm to 150 nm, and particularly preferably, is in the range from
50 nm to 100 nm, in order to reliably achieve a dark current
reducing capability and to prevent the photoelectric conversion
efficiency of the photoelectric transducer 512 from being
lowered.
[0347] For setting a bias voltage to move holes, which exist among
the electric charges generated in the photoelectric conversion film
512c, toward the lower electrode 512a, and to move electrons, which
exist among the electric charges generated in the photoelectric
conversion film 512c, toward the upper electrode 512b, the electron
blocking film and the hole blocking film may be switched in
position. Both the electron blocking film and the hole blocking
film are not necessarily required, and either one of them may be
included to provide a certain dark current reducing capability.
[0348] Each of the TFTs 518 of the TFT layer 510 includes a stacked
assembly of a gate electrode, a gate insulating film, and an active
layer (channel layer). A source electrode and a drain electrode are
disposed on the active layer and are spaced from each other with a
gap therebetween. The active layer may be made of any one of
amorphous silicon, an amorphous oxide, an organic semiconductor
material, and carbon nanotubes. However, the active layer is not
limited to being made from such materials.
[0349] Amorphous oxide, which the active layer may be made of,
preferably is an oxide (e.g., In--O oxide) including at least one
of In, Ga, and Zn, more preferably, is an oxide (e.g., In--Zn--O
oxide, In--Ga oxide, or Ga--Zn--O oxide) including at least two of
In, Ga, and Zn, and particularly preferably, is an oxide including
In, Ga, and Zn. An In--Ga--An--O amorphous oxide preferably is an
amorphous oxide the crystalline composition of which is represented
by InGaO.sub.3 (ZnO).sub.m where m represents a natural number
smaller than 6, and particularly preferably, is InGaZnO.sub.4. The
amorphous oxide, which the active layer may be made of, is not
limited to these materials.
[0350] The organic semiconductor material, which the active layer
may be made of, preferably is a phthalocyanine compound, pentacene,
vanadyl phthalocyanine, or the like, but is not limited to these
materials. The composition of such a phthalocyanine compound is
disclosed in detail in Japanese Laid-Open Patent Publication No.
2009-212389, and will not be described in detail below.
[0351] If the active layer of each of the TFTs 518 is made of one
of an amorphous oxide, an organic semiconductor material, and
carbon nanotubes, then the active layer is effective at reducing
noise generated in the radiation detector 502, because the active
layer does not absorb radiation 12 such as X-rays, or absorbs only
an extremely small amount of radiation 12.
[0352] If the active layer is made of carbon nanotubes, then the
TFTs 518 can have a high switching speed and exhibit a low
absorption rate for visible light in the TFTs 518. If the active
layer is made of carbon nanotubes, since the performance of the
TFTs 518 could be greatly degraded by trace metal impurities mixed
therewith, it is necessary to separate and extract highly pure
carbon nanotubes using a centrifugal separator or the like.
[0353] Films made of an organic photoelectric conversion material,
and films made of an organic semiconductor material are
sufficiently flexible. If the photoelectric conversion film 512c,
which is made of an organic photoelectric conversion material, and
the TFTs 518, the active layer of which is made of an organic
semiconductor, are combined, then the radiation detector 502, on
which the weight of the subject 18 is applied as a load, does not
necessarily need to be made highly rigid.
[0354] The insulating substrate 508 may be made of any material
insofar as the material is permeable to light and does not absorb a
significant amount of radiation 12. The amorphous oxide of the
active layer of the TFTs 518 and the organic photoelectric
conversion material of the photoelectric conversion film 512c of
the photoelectric transducer 512 can be deposited as films at low
temperatures. Therefore, the insulating substrate 508 is not
limited to a highly heat-resistant substrate, such as a
semiconductor substrate, a quartz substrate, a glass substrate, or
the like, but may be a flexible substrate made of synthetic resin,
a substrate of aramid fibers, or a substrate of bionanofibers. More
specifically, the insulating substrate 508 may be a flexible
substrate made of polyester such as polyethylene terephthalate,
polybutylene phthalate, polyethylene naphthalate, or the like,
polystyrene, polycarbonate, polyethersulfone, polyarylate,
polyimide, polycycloolefine, norbornene resin,
poly(chlorotrifluoroethylene), or the like. A flexible substrate
made of plastic enables the radiation detector 20 to be light in
weight and hence easy to carry around. The insulating substrate 508
may include an insulating layer for making the insulating substrate
508 electrically insulative, a gas barrier layer for making the
insulating substrate 508 impermeable to water and oxygen, and an
undercoat layer for making the insulating substrate 508 flat or to
facilitate intimate contact with the electrode.
[0355] Since a high-temperature process at 200 degrees Celsius may
be applied to aramid fibers, aramid fibers allow a transparent
electrode material to be set at a high temperature for providing
lower resistance. Such aramid fibers also allow driver ICs to be
automatically mounted thereon by a process including a solder
reflow process. Furthermore, inasmuch as aramid fibers have a
coefficient of thermal expansion close to ITO and glass, an
insulating substrate made of aramid fibers is less liable to warp
and crack after fabrication. In addition, an insulating substrate
made of aramid fibers may be made thinner than a glass substrate or
the like. Such an insulating substrate 508 may be in the form of a
stacked assembly made of an ultrathin glass substrate together with
aramid fibers.
[0356] Bionanofibers are made by compounding a bundle of cellulose
microfibrils (bacteria cellulose) produced by bacteria (acetic acid
bacteria, Acetobacter Xylinum) and a transparent resin. The bundle
of cellulose microfibrils has a width of 50 nm, which is 1/10 of
the wavelength of visible light, is highly strong and highly
resilient, and is subject to low thermal expansion. Bionanofibers
that contain 60% to 70% fibers and which exhibit a light
transmittance of about 90% at a wavelength of 500 nm can be
produced by impregnating bacteria cellulose with a transparent
resin such as an acrylic resin, an epoxy resin, or the like, and
setting the transparent resin. In addition to being flexible,
bionanofibers have a low coefficient of thermal expansion ranging
from 3 ppm to 7 ppm, which is comparable to silicon crystals, a
high strength of 460 MPa that matches the strength of steel, and a
high resiliency of 30 GPa. Therefore, an insulating substrate 508
made of bionanofibers can be thinner than glass substrates or the
like.
[0357] If a glass substrate is used as the insulating substrate
508, then the radiation detector 502 (TFT substrate) has an overall
thickness of about 0.7 mm, for example. According to the fourteenth
modification, the insulating substrate 508 comprises a thin
substrate made of a light-permeable synthetic resin in order to
make the cassette device 22 thinner. The overall thickness of the
insulating substrate 508 is reduced to about 0.1 mm, thereby making
the radiation detector 502 flexible. The radiation detector 502,
which is made flexible in this manner, increases the shock
resistance of the cassette device 22, such that the radiation
detector 502 is less liable to break even if the cassette device 22
is subjected to shocks. Plastic resins, aramid fibers,
bionanofibers, etc., do not absorb radiation 12 significantly.
Thus, if the insulating substrate 508 is made of any of the
aforementioned materials, the amount of radiation 12 absorbed by
the insulating substrate 508 can be reduced. Consequently, even
though radiation 12 passes through an ISS type of radiation
detector 502, a reduction in sensitivity to radiation 12 is
minimized.
[0358] The insulating substrate 508 of the cassette device 22 need
not necessarily comprise a substrate of synthetic resin, but may be
a substrate made of another material, such as a glass substrate or
the like.
[0359] A planarization layer 514 for planarizing the radiation
detector 502 is disposed on a side of the radiation detector 502
(TFT substrate), which is remote from the side (near the
scintillator 500) to which radiation 12 is applied.
[0360] According to the fourteenth modification, the radiation
detector 20 may be constructed in the following ways.
[0361] (1) The photoelectric transducer 512 including the PD may be
made of an organic photoelectric conduction material, and the TFT
layer 501 may comprise CMOS sensors. Since only the PD is made of
an organic material, the TFT layer 510 including the CMOS sensors
is not required to be flexible. The photoelectric transducer 512,
which is made of an organic photoelectric conduction material, and
the CMOS sensors are disclosed in Japanese Laid-Open Patent
Publication No. 2009-212377, and will not be described in detail
below.
[0362] (2) The photoelectric transducer 512 including the PD may be
made of an organic photoelectric conduction material, and the TFT
layer 501, which is flexible, may comprise a CMOS circuit having
TFTs made of an organic material. Pentacene may be used as a p-type
organic semiconductor material used in the CMOS circuit, and cupric
fluoride phthalocyanine (F.sub.16CuPc) may be used as an n-type
organic semiconductor material. Thus, the TFT layer 510 is made
flexible enough to achieve a smaller radius of curvature. With the
TFT layer 510 being constructed in this manner, the gate insulating
film may be made significantly thinner for thereby reducing the
drive voltage. The gate insulating film, the semiconductor, and the
electrodes may be fabricated at room temperature or at a
temperature of 100.degree. C. or lower. The CMOS circuit may be
fabricated directly on the flexible insulating substrate 508. The
TFTs, which are made of an organic material, can be microfabricated
by a fabrication process according to a scaling law. The insulating
substrate 508 can be formed as a flat substrate that is free of
surface irregularities by coating a thin polyimide substrate with a
polyimide precursor according to a spin-coating process, and
heating the coated substrate to change the polyimide precursor into
polyimide.
[0363] (3) The PDs and TFTs, which are made of crystalline Si, may
be disposed on a resin insulating substrate 508 according to a
fluidic self-assembly process for placing a plurality of micron
order device blocks in given positions on a substrate. More
specifically, the PDs and TFTs as minute device blocks on a micron
order are fabricated on another substrate, and then are cut off
from the substrate. Then, the PDs and TFTs are scattered over the
insulating substrate 508 as a target substrate and placed
statistically thereon. The insulating substrate 508 is processed to
match the device blocks, so that the device blocks can selectively
be placed on the insulating substrate 508. Therefore, optimum
device blocks (PDs and TFTs), which are made of an optimum
material, can be integrated on an optimum substrate (insulating
substrate 508). Therefore, it is possible to integrate PDs and TFTs
on a non-crystalline insulating substrate 508 (resin
substrate).
[Other Arrangements of the Present Exemplary Embodiment]
[0364] It is a matter of course that the present embodiment is not
limited to the arrangements described above.
[0365] More specifically, the radiographic image capturing
apparatus 10, 10A through 10M, and the radiographic image capturing
systems 11, 11A through 11M, which include the various
configurations described above, may also adopt the following
configurations listed below.
[0366] (1) A structure may be adopted having the radiation source
device 16, the cassette device 22, the web camera 30, and the
portable information terminal 34, in which the radiation source
device 16 and the portable information terminal 34 are constituted
separately from each other, and the web camera 30 is incorporated
in the portable information terminal 34 (see FIGS. 1 through 17,
and FIGS. 20, 22, 25 and 38).
[0367] (2) A structure may be adopted having the radiation source
device 16, the cassette device 22, the web camera 30, and the
portable information terminal 34, in which the radiation source
device 16 and the portable information terminal 34 are constituted
separately from each other, and the web camera 30 is incorporated
in the radiation source device 16 (see FIGS. 18 and 34).
[0368] (3) A structure may be adopted having the radiation source
device 16, the cassette device 22, the web camera 30, and the
portable information terminal 34, in which the radiation source
device 16 and the portable information terminal 34 are constituted
separately from each other, and the portable information terminal
34 and the web camera 30 are connected integrally via the USB cable
240 (see FIGS. 19 and 39).
[0369] (4) A structure may be adopted having the radiation source
device 16, the cassette device 22, the web camera 30, and the
portable information terminal 34, in which the radiation source
device 16 and the portable information terminal 34 are constituted
separately from each other, and the radiation source device 16 and
the web camera 30 are connected integrally via the USB cable 240
(see FIG. 40).
[0370] (5) A structure may be adopted having the radiation source
device 16, the cassette device 22, the web camera 30, and the
portable information terminal 34, in which the radiation source
device 16 and the portable information terminal 34 are constituted
separately from each other, and the web camera 30 also is
constituted separately from the radiation source device 16, the
cassette device 22, and the portable information terminal 34.
[0371] (6) A structure may be adopted having the radiation source
device 16, the cassette device 22, the web camera 30, and the
portable information terminal 34, in which the radiation source
device 16 and the portable information terminal 34 are constructed
integrally, and the web camera 30 is incorporated in the portable
information terminal 34 (see FIG. 21).
[0372] (7) A structure may be adopted having the radiation source
device 16, the cassette device 22, the web camera 30, and the
portable information terminal 34, in which the radiation source
device 16 and the portable information terminal 34 are constructed
integrally, and the web camera 30 is incorporated in the radiation
source device 16.
[0373] (8) A structure may be adopted having the radiation source
device 16, the cassette device 22, the web camera 30, and the
portable information terminal 34, in which the radiation source
device 16 and the portable information terminal 34 are constructed
integrally, and the web camera 30 is constituted separately from
the radiation source device 16, the cassette device 22, and the
portable information terminal 34.
[0374] (9) A structure may be adopted having the radiation source
device 16, the cassette device 22, and the web camera 30, and in
which the radiation source device 16 and the web camera 30 are
constituted separately from each other (see FIG. 23).
[0375] (10) A structure may be adopted having the radiation source
device 16, the cassette device 22, and the web camera 30, and in
which the radiation source device 16 and the web camera 30 are
constructed integrally with each other (see FIGS. 24, 31A and
32A).
[0376] In addition, in the foregoing configurations (1) through
(10), in the case that the communication unit 136 of the radiation
source device 16, the communication unit 170 of the cassette device
22, (the communication unit 218 of the portable information
terminal 34, the communication unit 262 of the high-voltage power
supply 252), and the communication unit 260 of the web camera 30
are provided, the camera image captured by the web camera 30 may be
transmitted from any one of such communication units, including the
communication unit 260 of the web camera 30, to the communication
unit 104 of the medical organization 40 via the network 36. In
other words, any one of such communication units functions as a web
camera communication unit for transmitting the camera image.
[0377] Further, in configurations (1) through (10), in the case
that the communication unit 136 of the radiation source device 16,
the communication unit 170 of the cassette device 22, (the
communication unit 218 of the portable information terminal 34, the
communication unit 262 of the high-voltage power supply 252), and
the communication unit 260 of the web camera 30 are provided, the
radiographic image output from the radiation detector 20 may be
transmitted from any one of such communication units, including the
communication unit 260 of the web camera 30, to the communication
unit 104 of the medical organization 40 via the network 36.
[0378] Accordingly, in configurations (1) through (10), in the
event that the communication unit 136 of the radiation source
device 16, the communication unit 170 of the cassette device 22,
(the communication unit 218 of the portable information terminal
34, the communication unit 262 of the high-voltage power supply
252), and the communication unit 260 of the web camera 30 are
provided, transmission and reception of signals via the network 36
between the radiographic image capturing apparatus 10, 10A through
10M and the communication unit 104 of the medical organization 40
can be carried out between the communication unit 104 and any one
of the other communication units, including the communication unit
260 of the web camera 30.
[0379] Furthermore, in the above exemplary embodiments, signals are
sent and received by way of at least one of wireless communications
and wired communications. However, if the subject 18 is held in
contact with the radiation source device 16 and the cassette device
22 with a short SID, then signals (e.g., a synchronization control
signal) may be sent and received between the radiation source
device 16 and the cassette device 22 by way of intrabody
communications through the subject 18. Further, as in the case of
modifications 11 through 13 (see FIGS. 34 through 40), if the
operator 32 is held in contact with both the radiation source
device 16 and the portable information terminal 34, then signals
may be sent and received between the radiation source device 16 and
the portable information terminal 34 by way of intrabody
communications through the operator 32.
[0380] The present invention is not limited to the above exemplary
embodiments, and it is a matter of course that various additional
or alternative arrangements may be adopted without departing from
the scope of the invention.
* * * * *