JP2009226201A - Radiation image capturing system, radiation image capturing method and program - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To provide a radiation image capturing system for displaying radiation images captured by image capturing apparatuses of different specifications with same size. <P>SOLUTION: The radiation image capturing system 10 includes: a first image capturing apparatus 22 for capturing a radiation image of a subject 50; a second image capturing apparatus 24 for capturing a radiation image of the subject 50, the second image capturing apparatus 24 having a specification different from that of the first image capturing apparatus 22; an image processing part 44 for correcting the radiation image which is captured by the second image capturing apparatus 24 so that the image captured by the first image capturing apparatus 22 has the same magnification as that of the radiation image captured by the second image capturing apparatus 24; and a display part 48 for displaying the corrected radiation image. Even radiation images different in image capturing condition are easily compared with one another and appropriate evaluation is provided by correcting radiation images captured by the image capturing apparatuses different in specifications to have the same magnification. <P>COPYRIGHT: (C)2010,JPO&INPIT

Description

  The present invention relates to a radiographic image capturing system, a radiographic image capturing method, and a program for correcting a magnification of a radiographic image captured by a plurality of imaging devices having different specification forms.

  2. Description of the Related Art In the medical field, imaging apparatuses that irradiate a subject with radiation and guide the radiation transmitted through the subject to a radiation detector to take a radiation image are widely used.

  In this case, as a radiation detector, a stimulable phosphor panel is known in which radiation energy as a radiation image is accumulated in the phosphor and the radiation image can be extracted as stimulated emission light by irradiating excitation light. . The stimulable phosphor panel on which the radiation image is recorded is supplied to a reading device and subjected to reading processing, whereby a radiation image as a visible image can be obtained.

  Further, in a medical field such as an operating room, it is required that the radiation image information can be read and displayed immediately from the radiation detector in order to perform a quick and accurate treatment on the patient. Radiation detection using a solid state detector that converts radiation directly into an electrical signal, or converts radiation into visible light with a scintillator, and then converts it into an electrical signal and reads it out A vessel has been developed.

  There are various types of imaging apparatuses that use these radiation detectors to capture radiographic images with different specifications according to imaging conditions such as the condition of the patient as the subject and the imaging region. It is controlled by a processing device having a specification form corresponding to the specification form. These imaging devices and processing devices are connected to a radiology information system (RIS) via an in-hospital network, and the patient information, imaging method, imaging site, imaging conditions that define the radiation dose, etc. set in the RIS are processed. There is a system in which a radiographic image is captured using a corresponding imaging apparatus (see Patent Document 1).

  Using this system, for example, when imaging the site of interest of the same patient regularly and for follow-up, it is essential that the same imaging device and imaging conditions be used. Depending on the change in the image quality and the usage status of the imaging device, it may not be possible to capture images with the same imaging device. For example, in the case of a patient who is difficult to walk, the imaging device is different when imaging is performed while lying on a bed and imaging is performed in a standing position when the same patient is able to walk later. In such a case, the radiographic images captured by different imaging devices are obtained when the distance between the subject and the radiation detector is different or the image processing method for the captured radiographic images is different. Therefore, it is difficult to accurately compare radiographic images as they are.

  As a conventional technique for processing a radiographic image in relation to a subject, a device for processing and displaying a radiographic image photographed by an imaging device so as to be the same size as the subject (see Patent Document 2), a reference having a known size An apparatus (see Patent Document 3) that captures a member and a subject at the same time and obtains the size and area of the subject from a radiographic image of the obtained reference member is known.

JP 2006-247137 A JP-A-7-265286 JP 2004-144651 A

  However, the prior art disclosed in Patent Document 2 only displays a radiographic image of a subject in actual size, and does not match radiographic images captured using different imaging devices. The prior art disclosed in Patent Document 3 can determine the size of a subject, but, as in Patent Document 2, does not match the scales of radiographic images.

  An object of the present invention is to provide a radiographic image capturing system, a radiographic image capturing method, and a program capable of displaying radiographic images captured by imaging apparatuses having different specification forms at the same magnification.

  A radiographic image capturing system according to a first aspect of the present invention includes a first image capturing device that captures a radiographic image of a subject, a second image capturing device that differs from the first image capturing device in a specification form for capturing a radiographic image of the subject, An image correction device that corrects the radiographic image of the subject imaged by the second imaging device so that the radiographic image of the subject imaged by the first imaging device is the same magnification, and the corrected radiographic image is displayed. And a display device.

  A radiographic image capturing method according to a second aspect of the present invention includes a first imaging device that captures a radiographic image of a subject, a second imaging device that has a specification form that captures a radiographic image of the subject, and is different from the first imaging device, In a radiographic imaging method used in a radiographic imaging system having a display device that displays the radiographic image, the step of acquiring radiographic image information of the subject using the first imaging device, and the second imaging The step of acquiring radiographic image information of the subject using an apparatus, and the radiographic image of the subject acquired by the second imaging device at the same magnification as the radiographic image of the subject acquired by the first imaging device And a step of displaying the corrected radiation image on the display device.

  A program according to a third aspect of the present invention includes a first imaging device that captures a radiographic image of a subject, a second imaging device that differs from the first imaging device in a specification form for capturing a radiographic image of the subject, and the radiographic image Means for acquiring radiographic image information of a subject using the first imaging device, and means for acquiring radiographic information of the subject using the second imaging device. Means for correcting the radiographic image of the subject acquired by the second imaging device so that the radiographic image of the subject acquired by the first imaging device is the same magnification as the radiographic image of the subject. It is a program for functioning as means for displaying on a display device.

  In the present invention, radiographic images captured by imaging apparatuses having different specification forms are displayed with the same magnification correction, so that radiation images with different imaging conditions can be easily compared and appropriately evaluated. Can do.

It is a block diagram of the radiographic imaging system of this embodiment. It is a typical explanatory view of a radiographic imaging system. It is a block diagram of the configuration including a host console, a first imaging device, and a second imaging device of the radiographic imaging system. It is a circuit block diagram of the radiation detector of this embodiment. It is a block diagram of the reading apparatus of this embodiment. It is a flowchart which shows the operation | movement outline | summary of a radiographic imaging system. It is a flowchart which shows the operation | movement with a 1st imaging device. It is a flowchart which shows the operation | movement with a 2nd imaging device. It is explanatory drawing of the positional relationship of the to-be-photographed object, marker part, and radiation detector in a 1st imaging device. It is explanatory drawing of the positional relationship of the to-be-photographed object, marker part, and stimulable fluorescent substance panel in a 2nd imaging device. It is a flowchart which shows the magnification correction | amendment in the control part of a host console.

  FIG.1 and FIG.2 shows the structure of the radiographic imaging system 10 of this embodiment. The radiographic imaging system 10 includes a medical information system 12 (HIS: Hospital Information System) that manages medical paperwork in a hospital, and radiology information that manages radiographic imaging processing in the radiology department under the control of the HIS 12. System 14 (RIS: Radiology Information System), viewer 15 for performing diagnostic interpretation by a doctor, and host console that is installed in a processing room adjacent to a radiology imaging room and manages various imaging apparatuses with different specification forms 16 (image correction device), a first console 18 and a second console 20 which are installed in the processing chamber and manage and control a specific imaging device, a first imaging device 22 controlled by the first console 18, 2 controlled by console 20 A second image capturing apparatus 24 is controlled by the second console 20, and a reader 26 reads the radiation image information captured by the second image capturing apparatus 24, which are connected to each other by in-house network 28. The in-hospital network 28 can be connected with other consoles, photographing devices, and the like as necessary.

  The host console 16 uses the HIS 12 to set patient information such as the patient's name, sex, and age, the radiographic image capturing method for the patient set by the doctor or engineer using the RIS 14, the imaging region, and the imaging used for imaging. The imaging instruction information of the apparatus or the like is acquired via the in-hospital network 28, and the information is supplied to the corresponding first console 18 or second console 20. Further, the host console 16 can also perform processing by the first console 18 or the second console 20. Therefore, by replacing the first console 18 or the second console 20 with the host console 16, a cheaper system configuration can be obtained. Connected to the host console 16 and the second console 20 are barcode readers 30 and 32 for acquiring ID information for specifying a radiation detector applied to a first imaging device 22 described later.

  FIG. 3 is a configuration block diagram of the host console 16, the first imaging device 22, and the second imaging device 24.

  The control unit 34 of the host console 16 receives necessary information between the RIS 14, the first console 18, the second console 20, the first imaging device 22, the second imaging device 24, and the reading device 26 via the hospital network 28. Send and receive. The host console 16 sets the shooting instruction information using the operation setting unit 36 and the operation setting unit 36 or receives the shooting instruction information set by the RIS 14 and stores it in the shooting instruction information memory 38. In accordance with the unit 40 and the set imaging instruction information, the specific first console 18 or the second console 20 that processes the radiation image information is selected, and the corresponding first imaging instruction information or the second console 18 is selected. Image processing unit 44 (image correction device) that performs image processing including magnification correction on the radiographic image information acquired from the first imaging device 22 and the second imaging device 24, and a console selection unit 42 to be supplied to the image processing unit 20. Image memory 45 for storing the radiation image information, and radiation before correction acquired from the first imaging device 22 and the second imaging device 24 It includes an image memory 46 for storing image information, a display unit 48 for displaying the radiation image information processed and (display device).

  The first console 18 and the second console 20 have substantially the same functions as the host console 16 except for the control unit 34 having a function of acquiring imaging instruction information from the RIS 14 and the console selection unit 42. Note that the host console 16, the first console 18, and the second console 20 do not necessarily have different configurations, and may have the same configuration.

  The first imaging device 22 is a standing imaging device that captures a radiation image of the chest of the subject 50, and a radiation detector using a radiation source 64 controlled by a radiation source control unit 66 and a solid-state detection element described later. 70 and an imaging table 60 disposed opposite to the radiation source 64. On the imaging stand 60, a marker unit 61 is formed at the same imaging position as the subject 50 and is photographed together with the subject 50. The radiation source control unit 66 drives and controls the radiation source 64 in accordance with the imaging conditions set by the host console 16.

  FIG. 4 shows a circuit configuration of the radiation detector 70 housed in the imaging table 60.

  In the radiation detector 70, a photoelectric conversion layer 72 made of a substance such as amorphous selenium (a-Se) that senses radiation and generates charges is arranged on an array of thin film transistors (TFTs) 74. After the generated charge is stored in the storage capacitor 76, the TFT 74 is sequentially turned on for each row, and the charge is read out as an image signal. In FIG. 4, only the connection relationship between one pixel 78 including the photoelectric conversion layer 72 and the storage capacitor 76 and one TFT 74 is shown, and the configuration of the other pixels 78 is omitted. Amorphous selenium must be used within a predetermined temperature range because its structure changes and its function decreases at high temperatures. Therefore, it is preferable to provide means for cooling the radiation detector 70 in the imaging table 60.

  To the TFT 74 connected to each pixel 78, a gate line 80 extending in parallel with the row direction and a signal line 82 extending in parallel with the column direction are connected. Each gate line 80 is connected to a line scanning drive unit 84, and each signal line 82 is connected to a multiplexer 86 constituting a reading circuit.

  Control signals Von and Voff for controlling on / off of the TFTs 74 arranged in the row direction are supplied from the line scanning drive unit 84 to the gate line 80. In this case, the line scanning drive unit 84 includes a plurality of switches SW1 for switching the gate lines 80, and an address decoder 88 for outputting a selection signal for selecting one of the switches SW1. An address signal is supplied from the control unit 100 to the address decoder 88.

  Further, the charge held in the storage capacitor 76 of each pixel 78 flows out to the signal line 82 via the TFTs 74 arranged in the column direction. This charge is amplified by the amplifier 92. A multiplexer 86 is connected to the amplifier 92 via a sample and hold circuit 94. The multiplexer 86 includes a plurality of switches SW2 for switching the signal line 82 and an address decoder 96 for outputting a selection signal for selecting one of the switches SW2. An address signal is supplied from the control unit 100 to the address decoder 96. An A / D converter 98 is connected to the multiplexer 86, and radiation image information converted into a digital signal by the A / D converter 98 is supplied to the control unit 100. The control unit 100 supplies the acquired radiation image information to the first console 18 that controls the first imaging device 22 via the in-hospital network 28.

  The second imaging device 24 is a standing imaging device that captures a radiation image of the subject 50 such as the chest, and the radiation source 104 controlled by the radiation source control unit 102 and the imaging disposed opposite to the radiation source 104. And the base 108. A marker unit 109 is formed on the photographing stand 108 at the same photographing position as the subject 50 and photographed together with the subject 50. The marker unit 109 formed on the imaging table 108 has the same dimensions and the same shape as the marker unit 61 formed on the imaging table 60 of the first imaging device 22. A slot 112 in which a cassette 110 containing the stimulable phosphor panel P is loaded is disposed on the side of the imaging stand 108. The second imaging device 24 is controlled by the second console 20 via the hospital network 28. The second imaging device 24 is different in specification form from the first imaging device 22. The radiation source control unit 102 drives and controls the radiation source 104 according to the imaging conditions set by the host console 16.

  In the stimulable phosphor panel P, a stimulable phosphor layer for accumulating the energy of the irradiated radiation X is formed on a support, and stimulated emission corresponding to the energy accumulated by irradiating excitation light. While outputting light, the remaining energy can be removed and reused by irradiating a predetermined amount of erasing light.

  The cassette 110 accommodates the stimulable phosphor panel P so as to be detachable via the lid member 114, and the outer surface portion thereof individually identifies the stimulable phosphor panel P accommodated therein. A barcode 116 in which identification information such as a unique number, a size, and sensitivity is recorded is attached. The barcode 116 can be read by the barcode reader 32 connected to the second console 20 or the barcode reader 30 connected to the host console 16.

  The radiation image information recorded on the stimulable phosphor panel P is read by the reading device 26 configured as shown in FIG. The reading device 26 is controlled by the second console 20 together with the second photographing device 24.

  The reading device 26 includes a cassette loading unit 120 at an upper portion of the casing 118, and stores a stimulable phosphor panel P in which radiation image information is accumulated and recorded in a loading port 122 formed in the cassette loading unit 120. The cassette 110 is loaded. A barcode reader 124 that reads the identification information of the barcode 116 disposed in the cassette 110, a lock release mechanism 126 that unlocks the lid member 114 of the cassette 110, and a lid member 114 are provided near the loading port 122. An adsorption board 128 that adsorbs and takes out the stimulable phosphor panel P from the opened cassette 110 and a nip roller 130 that sandwiches and conveys the stimulable phosphor panel P taken out by the adsorption board 128 are disposed.

  A plurality of transport rollers 132 a to 132 g and a plurality of guide plates 134 a to 134 f are arranged in series with the nip roller 130, and a curved transport path 136 is configured by these. The curved conveyance path 136 extends downward from the cassette loading unit 120, then becomes substantially horizontal at the lowermost portion, and then extends substantially vertically upward. Thereby, size reduction of the reader 26 is achieved.

  Between the nip roller 130 and the conveying roller 132a, an erasing unit 138 for erasing the radiation image information remaining on the stimulable phosphor panel P that has been read is disposed. The erasing unit 138 includes an erasing light source 140 such as a cold cathode tube that outputs erasing light.

  A platen roller 142 is disposed between the transport rollers 132d and 132e disposed at the lowermost portion of the curved transport path 136. A scanning unit 144 that reads radiation image information accumulated and recorded on the stimulable phosphor panel P is disposed on the platen roller 142.

  The scanning unit 144 derives a laser beam LB that is excitation light and scans the stimulable phosphor panel P, and stimulated emission light related to radiation image information that is excited and output by the laser beam LB. A reading unit 148 for reading.

  The excitation unit 146 reflects a laser oscillator 150 that outputs a laser beam LB, a polygon mirror 152 that is a rotary polygon mirror that deflects the laser beam LB in the main scanning direction of the stimulable phosphor panel P, and the laser beam LB. And a reflecting mirror 154 that leads to the stimulable phosphor panel P that passes over the platen roller 142.

  The reading unit 148 is connected to the condensing guide 156 disposed at one end close to the stimulable phosphor panel P on the platen roller 142 and the other end of the condensing guide 156. A photomultiplier 158 that converts the stimulated emission light obtained from the above into an electrical signal. Note that a condensing mirror 160 for increasing the condensing efficiency of the photostimulated luminescent light is disposed close to one end of the condensing guide 156. The radiographic image information read by the photomultiplier 158 is supplied to the second console 20 via the hospital network 28.

  The in-hospital network 28 can be connected to a supine imaging device using the radiation detector 70 or the stimulable phosphor panel P. The hospital network 28 can be connected with imaging devices of other specification forms, for example, CT devices and MR devices, and can be connected with a console for controlling these imaging devices.

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

  First, patient information such as the patient's name, sex, and age is set using the HIS 12 (step S1 in FIG. 6). Next, in relation to the patient information, a radiographic imaging method, imaging site, and imaging are performed. Shooting instruction information such as a shooting apparatus to be used is set using the RIS 14 (step S2).

  The control unit 34 of the host console 16 installed in the radiology department acquires patient information and imaging instruction information from the RIS 14 via the in-hospital network 28 (step S3). The engineer uses the operation setting unit 36 of the host console 16 to change and set the shooting instruction information as necessary. For example, the imaging device set by the doctor using the RIS 14 is changed to an imaging device corresponding to the imaging region or the patient's condition. The imaging instruction information setting unit 40 temporarily stores the acquired patient information and imaging instruction information, or changed or newly set imaging instruction information in the imaging instruction information memory 38.

  Next, the imaging instruction information setting unit 40 of the host console 16 reads out patient information and imaging instruction information from the imaging instruction information memory 38 (step S4). The console selection unit 42 is connected to the first console 18 that controls the corresponding first imaging device 22, the second console 20 that controls the second imaging device 24, or the hospital network 28 according to the read imaging instruction information. The corresponding other console is selected (step S5).

  In this case, the console selection unit 42 determines whether or not the processing device that controls the imaging device specified by the imaging instruction information is in a processable state. For example, the corresponding processing device controls the imaging device to perform imaging processing, or the corresponding processing device performs image processing on radiation image information acquired from the imaging device, and immediately executes the next imaging processing When the processing state is not possible, the processing device is determined to be in a state incapable of processing. Further, when the corresponding processing device or the imaging device controlled by the processing device is in a failure state, it is determined that the processing device is in an unprocessable state. When it is determined that the corresponding processing apparatus cannot be processed, the console selection unit 42 searches for another processing apparatus that can perform the imaging process according to the imaging instruction information and is in a processable state.

  After the processing device in the processable state is selected, the control unit 34 of the host console 16 transmits the shooting instruction information to the selected first console 18, the second console 20, or another console (step S6). After confirming that the transmission has been completed, the patient information and the imaging instruction information in the imaging instruction information memory 38 are deleted.

  When the host console 16 is a processing device that can perform processing of a plurality of photographing devices having different specification forms, the host console 16 is replaced with the first photographing device 22 instead of the first console 18 or the second console 20. Alternatively, the second imaging device 24 can be selected as a console for processing.

  The console to which the patient information and the imaging instruction information are transmitted performs a radiographic image imaging process using an imaging apparatus under management in accordance with the imaging instruction information (step S7).

  First, the case where the first photographing device 22 is controlled using the first console 18 to photograph the subject 50 will be described with reference to the flowchart of FIG.

  The first console 18 that has received the imaging instruction information from the host console 16 instructs the radiation source control unit 66 of the first imaging apparatus 22 to perform tube voltage, tube current, and radiation irradiation time, which are imaging conditions included in the imaging instruction information. Is set (step S101 in FIG. 7).

  Next, after the subject 50 is positioned at a predetermined position on the photographing stand 60, photographing is started by operating an exposure switch (not shown) (step S102). The radiation source control unit 66 drives and controls the radiation source 64 according to the set imaging conditions, and irradiates the subject 50 with the radiation X (step S103). The radiation X that has passed through the subject 50 is irradiated to the radiation detector 70. In addition, a marker unit 61 is formed on the imaging table 60 at the same position as the imaging surface of the subject 50, and the radiation X transmitted through the marker unit 61 is transmitted to the radiation detector 70 together with the radiation X transmitted through the subject 50. Irradiated.

  The photoelectric conversion layer 72 of each pixel 78 (see FIG. 4) constituting the radiation detector 70 converts the incident radiation X into an electrical signal, and the electrical signal is held in the storage capacitor 76 as a charge. Next, the charge information which is radiation image information of the subject 50 and the marker unit 61 held in each storage capacitor 76 is read according to an address signal supplied from the control unit 100 to the line scanning drive unit 84 and the multiplexer 86.

  That is, the address decoder 88 of the line scan driver 84 outputs a selection signal in accordance with the address signal supplied from the controller 100 to select one of the switches SW1, and the gate of the TFT 74 connected to the corresponding gate line 80. Is supplied with a control signal Von. On the other hand, the address decoder 96 of the multiplexer 86 outputs a selection signal in accordance with the address signal supplied from the control unit 100 to sequentially switch the switch SW2, and each pixel connected to the gate line 80 selected by the line scan driving unit 84. Radiation image information as charge information held in the storage capacitor 76 of 78 is sequentially read out via the signal line 82.

  The radiation image information read from the storage capacitor 76 of each pixel 78 connected to the selected gate line 80 of the radiation detector 70 is amplified by each amplifier 92 and then sampled by each sample and hold circuit 94. The signal is supplied to the A / D converter 98 via the multiplexer 86 and converted into a digital signal. The radiographic image information converted into the digital signal is transmitted by the control unit 100 to the first console 18 via the in-hospital network 28 (step S104).

  Similarly, the address decoder 88 of the line scan driving unit 84 sequentially switches the switch SW1 according to the address signal supplied from the control unit 100, and is held in the storage capacitor 76 of each pixel 78 connected to each gate line 80. The radiographic image information as the charge information is read out via the signal line 82 and transmitted to the first console 18 via the multiplexer 86, the A / D converter 98 and the control unit 100 (step S104).

  The first console 18 performs image processing according to the specifications of the first imaging device 22 on the received radiation image information, displays and confirms the radiation image as necessary, and then via the hospital network 28, The radiographic image information D1 subjected to the image processing related to the subject 50 and the marker unit 61 is transmitted to the host console 16. The control unit 34 of the host console 16 temporarily stores the radiation image information D1 in the image memory 46.

  Next, a case where the second imaging device 24 is controlled using the second console 20 to perform chest imaging of the subject 50 will be described with reference to the flowchart of FIG.

  The second console 20 that has received the imaging instruction information from the host console 16 instructs the radiation source control unit 102 of the second imaging apparatus 24 to perform tube voltage, tube current, and radiation irradiation time, which are imaging conditions included in the imaging instruction information. Is set (step S201 in FIG. 8).

  On the other hand, the technician reads the barcode attached to the cassette 110 using the barcode reader 32 connected to the second console 20 to identify the stimulable phosphor panel P housed in the cassette 110. For this purpose, identification information such as a unique number, size, and sensitivity is acquired (step S202).

  Next, after the cassette 110 is loaded into the slot 112 of the second imaging device 24, an exposure switch (not shown) is operated to start imaging (step S203). The radiation source control unit 102 drives and controls the radiation source 104 according to the set imaging conditions, and irradiates the subject 50 with the radiation X (step S204). The radiation X transmitted through the subject 50 is applied to the stimulable phosphor panel P housed in the cassette 110. As a result, the radiation image information of the subject 50 is accumulated and recorded on the stimulable phosphor panel P.

  In addition, a marker unit 109 is formed on the imaging table 108 at the same position as the imaging surface of the subject 50, and the radiation X transmitted through the marker unit 109 together with the radiation X transmitted through the subject 50 is a stimulable phosphor panel. P is irradiated.

  The cassette 110 that stores the stimulable phosphor panel P on which the radiation image information is recorded is extracted from the second imaging device 24 and then loaded into the cassette loading unit 120 of the reading device 26.

  When the cassette 110 is loaded, the barcode reader 124 disposed in the cassette loading unit 120 reads the barcode attached to the cassette 110 and identifies the unique number, size, sensitivity, etc. of the stimulable phosphor panel P. Get information. The acquired identification information is collated with the identification information acquired by the bar code reader 32 connected to the second console 20 to confirm the correspondence between the subject 50 and the radiation image information.

  When the identification information is read, the lock release mechanism 126 is driven, and the cover member 114 is unlocked and opened. Next, the suction disk 128 sucks the stimulable phosphor panel P, takes out the stimulable phosphor panel P from the cassette 110, and supplies it between the nip rollers 130. The stimulable phosphor panel P sandwiched between the nip rollers 130 is transported to the lower part of the scanning unit 144 via a curved transport path 136 including transport rollers 132a to 132g and guide plates 134a to 134f.

  The stimulable phosphor panel P is sub-scanned and conveyed in the substantially horizontal direction by the conveying rollers 132d and 132e. On the other hand, the laser beam LB output from the laser oscillator 150 constituting the excitation unit 146 is reflected and deflected by the polygon mirror 152 that rotates at high speed, and then the lower surface is supported by the platen roller 142 via the reflection mirror 154. Guided to the stimulable phosphor panel P, the stimulable phosphor panel P is main-scanned.

  The stimulable phosphor panel P is excited by being irradiated with the laser beam LB and outputs stimulated emission light according to the stored and recorded radiation image information. This stimulated emission light is directly incident on the lower end portion of the condensing guide 156 disposed close to the stimulable phosphor panel P along the main scanning direction, or is incident through the condensing mirror 160. The stimulated emission light incident on the light collecting guide 156 is repeatedly reflected inside and guided to the photomultiplier 158 at the upper end. The photomultiplier 158 converts the incident stimulated emission light into an electrical signal, thereby reading the radiographic image information of the subject 50 and the marker unit 109 accumulated and recorded in the stimulable phosphor panel P (step S205). ).

  The radiation image information read by the scanning unit 144 is transmitted to the second console 20 via the in-hospital network 28 (step S206). The second console 20 performs image processing according to the specifications of the second imaging device 24 on the received radiation image information, displays and confirms the radiation image as necessary, and then via the hospital network 28, The radiographic image information D2 subjected to the image processing related to the subject 50 and the marker unit 109 is transmitted to the host console 16 (step S207). The control unit 34 of the host console 16 temporarily stores the radiation image information D2 in the image memory 46 (step S208).

  Next, the control unit 34 reads out the radiation image information D1 acquired using the first imaging device 22 and the radiation image information D2 acquired using the second imaging device 24 from the image memory 46, and the image processing unit 44. To perform desired image processing. In this case, for example, radiographic images of the same subject 50 are captured at different times using the first imaging device 22 and the second imaging device 24, and the magnification of these radiographic images is corrected to the same magnification, and the display unit 48 is used. The process of displaying the information and performing a comparative diagnosis will be described with reference to FIGS.

  FIG. 9 is an explanatory diagram of the positional relationship among the subject 50, the marker unit 61, and the radiation detector 70 in the first imaging device 22, and FIG. 10 shows the subject 50 and the marker unit 109 in the second imaging device 24. And an explanatory diagram of a positional relationship with the stimulable phosphor panel P.

  The distance L1 from the imaging surface of the imaging table 60 with which the subject 50 of the first imaging device 22 abuts to the built-in radiation detector 70 and the imaging surface of the imaging table 108 with which the subject 50 of the second imaging device 24 abuts. The distance L2 from the storage phosphor panel P loaded in the cassette 110 to the storage phosphor panel P is usually different because the configurations of the first imaging device 22 and the second imaging device 24 are different. . Therefore, even when the same subject 50 is photographed, the radiographic images obtained by photographing have different sizes.

  Therefore, the image processing unit 44 uses the radiation image information of the marker unit 61 formed on the imaging surface of the imaging table 60 of the first imaging device 22 and the marker formed on the imaging surface of the imaging table 108 of the second imaging device 24. The radiographic image information of the unit 109 is read from the image memory 46, and the image areas S1 and S2 of the marker units 61 and 109 are calculated. Then, an area ratio S1 / S2 of these areas S1 and S2 is calculated (step S301 in FIG. 11).

  Next, for example, when the radiation image information D2 acquired from the second imaging device 24 is made to be the same size as the radiation image information D1 acquired from the first imaging device 22, the image processing unit 44 uses the radiation image information D2. A correction process is performed by multiplying the area ratio S1 / S2 (step S302). As a result, radiation image information D2 'having the same magnification as that of the radiation image information D1 can be obtained.

  The image processing unit 44 outputs and displays the radiation image information D2 'whose magnification has been adjusted as described above on the display unit 48 (step S303). The engineer can check the radiation image of the subject 50 displayed on the display unit 48. On the other hand, the radiation image information D2 ′ whose magnification has been adjusted and the radiation image information D1 whose magnification has not been adjusted are transmitted to the viewer 15 via the in-hospital network 28, and both of these radiation images are displayed. The doctor can make a comparative diagnosis of a desired part of the subject 50.

  A plurality of marker portions 61 and 109 are formed at a predetermined distance from the imaging stand 60 of the first imaging device 22 and the imaging stand 108 of the second imaging device 24, and the radiographic images of these marker portions 61 and 109 are formed. And the two radiation image information D1 and D2 may be corrected based on the distance ratio.

  In this embodiment, the host console 16 corrects the radiographic image at the same magnification. However, the image processing unit 44 and the image memory 46 are provided in one or both of the first console and the second console, so that the radiographic image is corrected. The same magnification correction may be performed.

  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.

  That is, as the radiation detector 70, a method (direct conversion method) in which the incident radiation X is directly converted into an electrical signal by the photoelectric conversion layer 72 is used. Instead, the incident radiation X is temporarily converted into visible light by a scintillator. A radiation detector that converts the visible light into an electrical signal using a solid-state detection element such as amorphous silicon (a-Si) may be used (indirect conversion method: Japanese Patent No. 3494683). reference). Furthermore, radiation image information can also be acquired using a light readout type radiation detector. In this optical readout type radiation detector, when radiation is incident on the solid detection elements arranged in a matrix, an electrostatic latent image corresponding to the dose is accumulated and recorded on the solid detection elements. 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. After the radiation image information is read, the radiation image information, which is a remaining electrostatic latent image, can be erased and reused by irradiating the radiation detector with erasing light (Japanese Patent Laid-Open No. 2000-105297). See the official gazette).

  In the radiation detector 70 described above, an example in which the TFT 74 is used has been described. However, the radiation detector 70 may be implemented in combination with another imaging element such as a CMOS (Complementary Metal-Oxide Semiconductor) image sensor. Furthermore, it can be replaced with a CCD (Charge-Coupled Device) image sensor that transfers charges while shifting the charges by a shift pulse corresponding to the gate signal referred to in the TFT 74. In the above example, patient information is acquired via the HIS 12, and imaging instruction information is acquired via the RIS 14. However, a keyboard or a coordinate input device connected to the host console or the console is also used. The patient information and the imaging instruction information may be directly input.

10 ... Radiation imaging system 12 ... HIS
DESCRIPTION OF SYMBOLS 14 ... RIS 16 ... Host console 18 ... 1st console 20 ... 2nd console 22 ... 1st imaging device 24 ... 2nd imaging device 26 ... Reading device 28 ... Hospital network 30, 32, 124 ... Barcode reader 38 ... Imaging | photography instruction | indication Information memory 40 ... Shooting instruction information setting unit 42 ... Console selection unit 44 ... Image processing unit 45, 46 ... Image memory 48 ... Display unit 50 ... Subject 61, 109 ... Marker unit

Claims (6)

A first imaging device for capturing a radiographic image of a subject;
A second imaging device having a specification form for capturing a radiographic image of the subject different from the first imaging device;
An image correction device that corrects the radiation image of the subject imaged by the second imaging device so as to be the same magnification as the radiation image of the subject imaged by the first imaging device;
A display device for displaying the corrected radiation image;
A radiographic imaging system comprising: In the radiographic imaging system of Claim 1,
The first photographing device and the second photographing device have a marker portion of the same shape that is photographed together with the subject,
The image correction apparatus corrects the radiographic image of the subject so that the radiographic images of the marker portions captured by the first imaging apparatus and the second imaging apparatus match. system. In the radiographic imaging system of Claim 1,
The image correction device corrects a radiographic image of the subject based on photographing position information on the subject in the first photographing device and photographing position information on the subject in the second photographing device. A radiographic imaging system. In the radiographic imaging system of Claim 3,
The first imaging device includes a first radiation detector that detects radiation transmitted through the subject and converts the radiation into a radiation image;
The second imaging device includes a second radiation detector that detects radiation transmitted through the subject and converts the radiation into a radiation image,
The imaging position information for the subject in the first imaging device is a distance from the imaging surface of the first imaging device to the first radiation detector,
The radiographic imaging system, wherein the imaging position information on the subject in the second imaging device is a distance from the imaging surface of the second imaging device to the second radiation detector. A radiographic image having a first imaging device that captures a radiographic image of a subject, a second imaging device that is different from the first imaging device in a specification form for capturing the radiographic image of the subject, and a display device that displays the radiographic image In the radiographic imaging method used in the imaging system,
Acquiring radiation image information of the subject using the first imaging device;
Obtaining radiation image information of the subject using the second imaging device;
Correcting the radiographic image of the subject acquired by the second imaging device so as to be the same size as the radiographic image of the subject acquired by the first imaging device;
And a step of displaying the corrected radiation image on the display device. A radiographic image having a first imaging device that captures a radiographic image of a subject, a second imaging device that is different from the first imaging device in a specification form for capturing the radiographic image of the subject, and a display device that displays the radiographic image Shooting system
Means for acquiring radiographic image information of the subject using the first imaging device;
Means for acquiring radiographic image information of the subject using the second imaging device;
Means for correcting the radiographic image of the subject acquired by the second imaging device so as to be the same magnification as the radiographic image of the subject acquired by the first imaging device;
Means for displaying the corrected radiation image on the display device;
Program to function as.

Images