JP5160991B2 - Radiation imaging system - Google Patents

Description

  The present invention relates to a radiographic imaging system that records radiation image information on a radiation conversion panel by irradiating the radiation conversion panel with radiation from a radiation source through a subject.

  2. Description of the Related Art In the medical field, a radiation image capturing system is widely used that irradiates a subject with radiation and guides the radiation transmitted through the subject to a radiation conversion panel to capture radiation image information. As the radiation conversion panel, for example, a stimulable phosphor panel that accumulates radiation energy as radiation image information in a phosphor, and can extract the radiation image information as stimulated emission light by irradiating with excitation light. Are known. In this case, a visible image can be obtained by supplying the storage phosphor panel on which the radiation image information is recorded to a reading device and performing a reading process.

  By the way, it is desired that radiographic image information can be efficiently captured for a subject during a round-trip in a hospital. Thus, Patent Document 1 proposes that a radiation source that outputs radiation is configured to be movable along a track (running rail) disposed on a ceiling in a hospital room. In Patent Document 2, an X-ray tube (radiation source) is fixed to one end of a C-arm connected to a movable X-ray imaging apparatus, and an image detection unit is detachably attached to the other end. It has been proposed to do.

JP 2008-86448 A JP-A-2005-470

  However, with the technique of Patent Document 1, it is difficult to configure the entire system at low cost because a radiation source must be arranged for each patient room in which the subject is present. In addition, it is necessary to change the target and filter constituting the radiation source according to the imaging region of the subject. However, the technique of Patent Document 1 intends to change the target and the filter according to the imaging region of the subject. Not done. Therefore, when changing the target and the filter according to the imaging region of the subject, a plurality of radiation sources different from each other in the target and the filter are mounted in advance on the trajectory, and depending on the imaging region of the subject. Therefore, it is necessary to select a radiation source used for the imaging process, which is expensive.

  On the other hand, in Patent Document 2, since the radiation source is fixed to the C-arm, the target and the filter cannot be changed according to the imaging region of the subject, and therefore the degree of freedom of the arrangement of the radiation source with respect to the subject. Is constrained.

  The present invention has been made to solve the above-described problems, and by easily changing the radiation source according to the imaging region of the subject, the degree of freedom in arranging the radiation source with respect to the subject is increased. An object of the present invention is to provide a radiographic imaging system that can be constructed at low cost.

  A radiation image capturing system according to the present invention is installed in a facility capable of capturing radiation image information, a radiation source that outputs radiation, the radiation source is detachable, and the arrangement of the radiation sources is adjusted. A movable arm member, a control device that controls the radiation source, a radiation conversion panel that records the radiation emitted from the radiation source through the subject as the radiation image information, and the control device are mounted and moved And a dolly configured to be possible.

  According to the present invention, the radiation source can be attached to and detached from the arm member, and the radiation source is attached to the arm member according to the imaging region of the subject at the round, and the radiographic image information is captured by the attached radiation source. Thus, the radiation source attached to the arm member can be easily changed according to the imaging region of the subject, and the degree of freedom of arrangement of the radiation source with respect to the subject can be increased. Further, since it is not necessary to install a radiation source for each patient room where the subject is present, the radiation source can be shared, and the entire system can be made inexpensive.

  As shown in FIG. 1, a radiographic imaging system 10 according to this embodiment includes a carriage 12 that can move in a hospital room or the like by providing wheels 14, a reading device 16 that is mounted on the carriage 12, and a console. 18. A cassette (radiation converter) that houses a display device 19, an X-ray source control device 20, transceivers 22a and 22b, a battery 24, an X-ray irradiation switch 94 to be described later, and a storage phosphor panel (radiation conversion panel) 38 36), a track 132 as a traveling rail disposed on a ceiling portion 130 of a facility such as a hospital room where the subject 34 is located, an arm member 140 attached to a base 138 attached to the track 132, and the arm member X-ray sources (radiation sources) 30a and 30b that can be mounted on a mounting member 142 attached to the front end portion of 140.

  The console 18 constituting the control device together with the X-ray source control device 20 inputs imaging conditions for imaging radiographic image information, or sets the imaging conditions by acquiring the imaging conditions from the outside. . The X-ray source control device 20 controls the X-ray source 30 a mounted on the mounting member 142 of the arm member 140 according to the imaging conditions supplied from the console 18. In this case, the X-ray source control device 20 is connected to the transceiver (transmission means) 22a, and the transceiver (reception means) 23 mounted on the track 132 is connected to the X-ray source 30a via the signal line 136. Therefore, the X-ray source control device 20 controls the X-ray source 30a via wireless communication between the transceivers 22a and 23 and wired communication using the signal line 136. The two X-ray sources 30 a and 30 b are radiation sources having different targets and filters, and the X-ray source 30 a or the X-ray source 30 b is mounted on the mounting member 142 according to the imaging region of the subject 34. 1 illustrates the case where the X-ray source 30a is mounted on the mounting member 142. In the following description, the case where the X-ray source 30a is mounted on the mounting member 142 will be mainly described.

  The base 138 is mounted so as to be movable along the track 132. Therefore, the arm member 140 attached to the base 138 can move along the track 132, and the arrangement of the X-ray source 30a attached to the attachment member 142 can be adjusted.

  As shown in FIGS. 1 and 2, a mounting member 142 to which the X-ray source 30 a is mounted is pivotally supported on the distal end side of the arm member 140. The mounting member 142 includes a U-shaped fixing member 154, two handles 156 disposed on the outer surface of the fixing member 154, and four recesses 158 formed inward of the fixing member 154. On the other hand, four projections 144 that can be fitted into the recesses 158 are formed on the side surface of the X-ray source 30a, and a connector 148 is disposed in the recess 146 formed on the upper surface of the X-ray source 30a. Yes.

  Here, when the X-ray source 30 a is mounted on the mounting member 142, the projections 144 of the X-ray source 30 a are fitted into the recesses 158 of the mounting member 142, respectively, and the signal line 136 and the power line 134 are connected to the connector 148. Are connected to each other. Therefore, power can be supplied from the power source 26 to the X-ray source 30 a mounted on the mounting member 142 via the power line 134 and the connector 148. In addition, the X-ray source 30 a can be controlled from the X-ray source control device 20 via the transceivers 22 a and 23, the signal line 136 and the connector 148.

  In FIG. 1, the X-ray source 30 a mounted on the mounting member 142 irradiates the subject 34 with X-rays 32 based on control from the X-ray source control device 20. The stimulable phosphor panel 38 in the cassette 36 accumulates and records X-rays 32 transmitted through the subject 34 as radiation image information. When the cassette 36 is loaded, the reading device 16 reads the radiation image information accumulated and recorded on the stimulable phosphor panel 38 accommodated in the cassette 36. The display device 19 displays a visible image based on the radiation image information read by the reading device 16. The transceiver 22b can acquire necessary information from the outside, and can further transmit the radiation image information read by the reading device 16 to the outside. The battery 24 supplies power to the console 18, the display device 19, the X-ray source control device 20, and the transceivers 22a and 22b. The battery 24 can be charged from the outside as necessary.

  As shown in FIG. 3, the cassette 36 loaded in the reading device 16 has a lid member 40 that can be freely opened and closed, and a barcode (not shown) on which ID information for identifying the cassette 36 is recorded. Yes.

  The reading device 16 includes a cassette loading unit 42 in the upper part of the casing 41, and a lid member 44 that is slidable in the direction of the arrow is disposed in the cassette loading unit 42. The cassette 36 in which the stimulable phosphor panel 38 in which the radiation image information is recorded is loaded into the cassette loading unit 42 with the lid member 40 facing down. The casing 41 is formed of a material containing heavy metal such as lead so as to prevent the entry of X-rays 32 (see FIG. 1) from the outside.

  The cassette loading unit 42 includes a barcode reader 46 that reads a barcode attached to the cassette 36, an unlocking mechanism 48 that unlocks the lid member 40 of the cassette 36, and a storage phosphor panel 38 from the cassette 36. An adsorbing board 50 that adsorbs and takes out the liquid and a nip roller 52 that sandwiches and conveys the stimulable phosphor panel 38 taken out by the adsorbing board 50 are disposed.

  A plurality of transport rollers 54 a to 54 g and a plurality of guide plates 56 a to 56 f are arranged in series with the nip roller 52, and the curved transport path 60 is configured by these. The curved conveyance path 60 extends downward from the cassette loading section 42, then becomes substantially horizontal at the bottom, and then extends substantially vertically upward. Note that each position of the curved conveyance path 60 functions as a retracting unit that retracts the stimulable phosphor panel 38 during imaging using the X-ray source 30. In addition, sensors 58 a to 58 d for detecting the stimulable phosphor panel 38 to be conveyed are disposed at predetermined portions of the curved conveyance path 60.

  Between the nip roller 52 and the conveyance roller 54a, an erasing unit 62 for erasing radiation image information remaining on the stimulable phosphor panel 38 that has been read is disposed. The erasing unit 62 has a plurality of erasing light sources 64 composed of cold cathode tubes that output erasing light.

  On the other hand, a platen roller 70 is disposed between the transport rollers 54d and 54e disposed at the lowermost portion of the curved transport path 60. A scanning unit 66 that reads the radiation image information accumulated and recorded on the stimulable phosphor panel 38 is disposed above the platen roller 70.

  The scanning unit 66 derives a laser beam 78 that is excitation light and scans the stimulable phosphor panel 38 in a direction (main scanning direction) orthogonal to the transport direction (sub-scanning direction), and the laser beam 78. And a photomultiplier for converting the photostimulated light collected by the light guide 72 into an electrical signal. 74. A condensing mirror 76 for increasing the condensing efficiency of the photostimulated luminescent light is disposed close to one end of the condensing guide 72.

  FIG. 4 is a control block diagram of the radiographic image capturing system 10. The X-ray source control device 20 drives the X-ray source 30a mounted on the mounting member 142 (see FIG. 1) by the operation of an operator such as a doctor or a radiographer, and the X-ray 32 is applied to a subject 34 such as a patient. An X-ray irradiation switch 94 for irradiation is connected.

  The reading device 16 includes a reading device control unit 80. The reading device control unit 80 includes a power switch 82 of the reading device 16, a cassette discharge button 88 for discharging the cassette 36 from the reading device 16, and a cassette 36. A bar code reader 46 for reading a bar code, a scanning unit controller 84 for controlling the scanning unit 66 (see FIG. 3), an erasing unit controller 86 for controlling the erasing unit 62, and a storage phosphor by controlling the curved conveyance path 60. The panel transport controller 90 that transports the panel 38 and the scanning unit 66 perform predetermined image processing on the radiation image information read from the stimulable phosphor panel 38, thereby allowing the operator to perform the display device 19. An image processing unit (image processing means) 92 that converts a visible image that can be confirmed is connected.

  The radiographic image capturing system 10 according to the present embodiment is basically configured as described above. Next, the operation thereof will be described with reference to FIGS.

  First, the operator moves the carriage 12 to a hospital room or the like where the subject 34 is located, and then attaches the X-ray source 30a corresponding to the imaging region of the subject 34 to the mounting member 142 and operates the handle 156 to operate the subject 34. In contrast, the X-ray source 30a is adjusted to a predetermined position. Next, the operator prepares for imaging after the radiographic imaging system 10 is turned on.

  In this case, the operator operates the console 18 to input the imaging condition such as the name of the subject 34 to be imaged during the round, the imaging method, or obtains the imaging condition from the outside via the transceiver 22b. The cassette 36 that records the radiographic image information of the subject 34 is selected, and the barcode information attached to the cassette 36 is read, whereby the ID information of the cassette 36 is acquired. In this way, when the imaging conditions and the ID information of the cassette 36 are set and preparation for imaging is completed, the X-ray source control device 20 outputs an imaging preparation completion signal to the reading device control unit 80 of the reading device 16.

  When the imaging preparation completion signal is input from the X-ray source control device 20, the reading device control unit 80 confirms whether or not the cassette 36 containing the stimulable phosphor panel 38 is loaded in the cassette loading unit 42. . The presence / absence of the cassette 36 can be determined, for example, by whether or not the barcode reader 46 disposed in the cassette loading unit 42 can read the barcode of the cassette 36.

  When it is determined that the cassette 36 is loaded in the cassette loading unit 42, the reader control unit 80 checks whether or not the stimulable phosphor panel 38 is accommodated in the cassette 36. In this case, in the reading device 16, only one storage phosphor panel 38 is supplied from the cassette 36 loaded in the cassette loading unit 42 to the inside of the casing 41 and processed. Therefore, for example, the panel conveyance control unit 90 does not control the curved conveyance path 60, or the sensors 58 a to 58 d disposed in predetermined portions of the curved conveyance path 60 detect the stimulable phosphor panel 38. If not, the reader control unit 80 can determine that the stimulable phosphor panel 38 is housed in the cassette 36.

  Here, when the stimulable phosphor panel 38 is accommodated in the cassette 36 loaded in the cassette loading unit 42 and the lid member 40 is closed, the locked state of the cassette 36 with respect to the cassette loading unit 42 is released. In addition, after the operation of the cassette ejection button 88, the operator can remove the cassette 36 from the cassette loading section 42 and place it directly under the subject 34 facing the X-ray source 30a as shown in FIG. it can. In this case, when the reader control unit 80 confirms that the stimulable phosphor panel 38 does not exist in the cassette loading unit 42, that is, the cassette 36 loaded with the stimulable phosphor panel 38 does not exist, the X-ray source A photographing permission signal is output to the control device 20.

  When a shot signal is input from the X-ray irradiation switch 94 due to the operator's operation after the imaging permission signal is input, the X-ray source control device 20 receives the transceivers 22a and 23, the signal line 136, and the connector. The X-ray source 30a is driven via 148 (see FIG. 2) to capture radiographic image information. At that time, electric power is supplied from the power source 26 to the X-ray source 30 a via the power line 134 and the connector 148. As a result, the X-rays 32 output from the X-ray source 30 a pass through the subject 34 and are irradiated onto the stimulable phosphor panel 38 housed in the cassette 36, and radiation image information is accumulated in the stimulable phosphor panel 38. To be recorded. When the imaging is completed, the X-ray source control device 20 outputs an imaging end signal to the reading device control unit 80.

  Next, the operator loads the reading device 16 with a cassette 36 containing a stimulable phosphor panel 38 on which radiation image information is accumulated and recorded. As a result, the barcode reader 46 reads the barcode attached to the cassette 36 to acquire the ID information of the cassette 36, and then the lock of the lid member 40 is released by the lock release mechanism 48 and the lid is opened. Next, the stimulable phosphor panel 38 in the cassette 36 is sucked and taken out by the suction board 50 and supplied to the curved conveyance path 60 by the nip roller 52. Conveying rollers 54 a to 54 g constituting the curved conveying path 60 convey the stimulable phosphor panel 38.

  The stimulable phosphor panel 38 is sub-scanned and transported between the transport rollers 54d and 54e, and the laser beam 78 from the excitation unit 68 scans the stimulable phosphor panel 38, thereby reading the radiation image information. Is called. That is, when the stimulable phosphor panel 38 is irradiated with the laser beam 78 output from the excitation unit 68, stimulated emission light corresponding to the radiation image information is output from the stimulable phosphor panel 38, and the stimulated emission is performed. The light is guided to the photomultiplier 74 via the light collection guide 72, converted into radiation image information as an electrical signal, and output to the image processing unit 92.

  The stimulable phosphor panel 38 from which the radiation image information has been read is once transported to the guide plate 56f side, and then returned to the cassette loading unit 42 side again through the lower portion of the scanning unit 66. The stimulable phosphor panel 38 returned to the cassette loading section 42 is accumulated by erasing light output from an erasing light source 64 that constitutes an erasing unit 62 disposed between the nip roller 52 and the conveying roller 54a. The radiation image information remaining on the fluorescent phosphor panel 38 is removed. The storable phosphor panel 38 that has been subjected to the erasing process of the remaining radiation image information is housed in the cassette 36 using the nip roller 52 and the suction disk 50 and the lid member 40 is closed, and then the cassette ejection button 88 is operated. As a result, it is extracted from the cassette loading section 42 and used for the next photographing.

  Next, the image processing unit 92 generates a visible image including the read radiation image information and the ID information of the cassette 36, and outputs the visible image to the display device 19 via the console 18 for display. The device 19 displays the visible image. The worker roughly grasps the state of the subject 34 based on the visible image displayed on the display device 19.

  The visible image generated by the image processing unit 92 is a radiology information system (RIS) that comprehensively manages radiographic image information and other information handled in the radiology department in the hospital by wireless communication from the transceiver 22b. ) Or a medical information system (HIS) that centrally manages medical information in the hospital.

  As described above, in the radiographic imaging system 10 according to the present embodiment, the X-ray sources 30a and 30b can be freely attached to and detached from the mounting member 142 attached to the distal end portion of the arm member 140. The X-ray sources 30a and 30b are attached to the mounting member 142 in accordance with the imaging part of the subject, and the radiographic image information is captured by the attached X-ray sources 30a and 30b, so that the mounting member 142 in accordance with the imaging part of the subject 34 is obtained. It is possible to easily change the X-ray sources 30a and 30b attached to the camera, and the degree of freedom of arrangement of the X-ray sources 30a and 30b with respect to the subject 34 can be increased. Further, since it is not necessary to install the X-ray sources 30a and 30b for each hospital room where the subject 34 is present, the X-ray sources 30a and 30b can be shared, and the entire system can be made inexpensive.

  Further, by mounting the reading device 16 for reading the radiation image information recorded on the stimulable phosphor panel 38 and the display device 19 for displaying the read radiation image information on the carriage 12, it is possible at the time of a roundabout in a hospital or the like. The worker can quickly grasp the state of the subject 34 quickly.

  Further, the carriage 12 includes a reading device 16, a console 18 for setting imaging conditions, a display device 19, and an X-ray source control device 20 for controlling the X-ray sources 30a and 30b mounted on the mounting member 142 based on the imaging conditions. And a battery 24 for supplying power to the transceivers 22a and 22b, and an X-ray source 30a mounted on the mounting member 142 from the power source 26 via the power line 134 and the connector 148. Since power is supplied to 30b, it is possible to easily perform imaging processing and reading processing of the subject 34 at the time of the round visit.

  Furthermore, the X-ray source control device 20 controls the X-ray sources 30a and 30b mounted on the mounting member 142 via the transceivers 22a and 23, the signal line 136, and the connector 148. Even if the carriage 12 on which the vehicle 20 is mounted and the X-ray sources 30a and 30b mounted on the mounting member 142 are separated from each other, the X-ray source 30a can be reliably controlled.

  In the above description, the cart 12 is equipped with two transceivers 22a and 22b. However, one transceiver may have the functions of the transceivers 22a and 22b. In the above description, power is supplied from the power supply 26 to the X-ray sources 30a and 30b mounted on the mounting member 142 via the power line 134 and the connector 148. However, instead of this configuration, transmission / reception is performed from the battery 24. Electric power may be supplied to the X-ray sources 30 a and 30 b mounted on the mounting member 142 via the machine 23, a power line (not shown) and the connector 148.

  In addition, this invention is not limited to embodiment mentioned above, Of course, it can change freely in the range which does not deviate from the main point of this invention.

  For example, instead of the stimulable phosphor panel 38, a radiation conversion panel having the following forms (1) to (3) using a semiconductor element may be applied.

  (1) A radiation detector (radiation conversion panel) having a structure in which a photoelectric conversion layer made of a material such as amorphous selenium (a-Se) that senses X-rays 32 and generates a charge is arranged on an array of thin film transistors. A radiation detector of a direct conversion system that converts a dose of X-rays 32 incident through a subject 34 during imaging into an electrical signal directly by the photoelectric conversion layer and outputs the converted electrical signal as radiation image information. Instead of the stimulable phosphor panel 38, the present invention is applied to a cassette 36 (electronic cassette).

  (2) Unlike the direct conversion method of (1) above, after the incident X-ray 32 is once converted into visible light by a scintillator, the visible light is converted into an electrical signal using a solid-state detection element such as amorphous silicon. An indirect conversion type radiation detector (see Japanese Patent No. 3494683) configured to output the converted electric signal as radiation image information is replaced with a storage phosphor panel 38 and a cassette 36 (electronic cassette). Applies to

  In the case of (1) and (2) above, the radiation detector outputs radiation image information. For example, by providing the cassette 36 or console 18 as an electronic cassette with the function of the image processing unit 92, The mounting of the reading device 16 on the carriage 12 can be omitted.

  (3) Radiation image information can also be acquired using a radiation detector of a light conversion method different from the methods (1) and (2). In this light conversion type radiation detector, when radiation is incident on each solid detection element (radiation conversion panel) arranged in a matrix, an electrostatic latent image corresponding to the dose is accumulated and recorded on the solid detection element. When reading the electrostatic latent image, the radiation detector is irradiated with reading light, and the value of the generated current is acquired as radiation image information (see Japanese Patent Application Laid-Open No. 2000-105297).

It is a block diagram of the radiographic imaging system which concerns on this embodiment. It is an expansion perspective view of the mounting member and X-ray source of FIG. It is an internal block diagram of the reader of FIG. It is a control block diagram of the radiographic imaging system of FIG.

Explanation of symbols

DESCRIPTION OF SYMBOLS 10 ... Radiation imaging system 12 ... Cart 16 ... Reading device 18 ... Console 19 ... Display device 20 ... X-ray source control device 22a, 22b, 23 ... Transmitter / receiver 24 ... Battery 26 ... Power source 30a, 30b ... X-ray source 32 ... X-ray 34 ... Subject 36 ... Cassette 38 ... Storage phosphor panel 130 ... Ceiling portion 132 ... Track 134 ... Power line 136 ... Signal line 140 ... Arm member 142 ... Mounting member 144 ... Protrusion 148 ... Connector 156 ... Handle 158 ... Recess

Claims (9)

A plurality of radiation sources with different targets and filters that can output radiation;
A traveling rail disposed on the ceiling of the facility capable of capturing radiation image information ;
A base mounted movably along the traveling rail;
An arm member attached to the base, a mounting member to which a radiation source corresponding to the imaging region of the subject can be attached and detached is attached to the tip portion , and the arrangement of the radiation source mounted to the mounting member is adjustable;
A control device for controlling the radiation source;
A radiation conversion panel for recording the radiation emitted from the radiation source through the subject as the radiation image information,
A carriage mounted with the control device and configured to be movable;
Transmitting means mounted on the carriage;
Receiving means attached to the traveling rail and connectable to the radiation source attached to the attachment member via a signal line;
I have a,
The control apparatus controls the radiation source mounted on the mounting member via wireless communication between the transmitting unit and the receiving unit and wired communication using the signal line. system. The system of claim 1, wherein
A radiographic imaging system, further comprising a reading device mounted on the carriage and reading the radiographic image information recorded on the radiation conversion panel. The system of claim 2, wherein
A radiographic image capturing system further comprising a display device mounted on the carriage and displaying the read radiographic image information. The system of claim 3, wherein
A radiographic imaging system, further comprising a battery mounted on the carriage and supplying power to the control device, the reading device, and the display device. The system according to any one of claims 1 to 4,
The control device includes a console for setting predetermined imaging conditions, and a radiation source control device for controlling the radiation source mounted on the mounting member based on the imaging conditions set by the console. A radiographic imaging system characterized by The system of claim 5 , wherein
Before Symbol radiation source controller, based on the imaging condition, the transmitting means, said receiving means and via the signal line radiation image capturing, characterized by controlling the radiation source mounted to the mounting member system. The system according to any one of claims 1 to 6,
The radiographic imaging system further comprising a power source for supplying power to the radiation source mounted on the arm member. The system according to any one of claims 1 to 7,
The radiation image capturing system, wherein the radiation conversion panel is a stimulable phosphor panel. The system according to any one of claims 1 to 7,
The radiation conversion panel converts the radiation irradiated through the subject into an electrical signal, and outputs the converted electrical signal as the radiation image information, or irradiated through the subject. A radiation image capturing system, wherein the radiation image is a radiation conversion panel in which the radiation is accumulated and recorded as an electrostatic latent image.

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