JP2007316408A - Radiation image recording/reading apparatus - Google Patents

Abstract

<P>PROBLEM TO BE SOLVED: To suppress a noise signal generated resulting from the light emission switching among linear light emitters, in a radiation image recording/reading apparatus including: a radiation image detector that records the radiation image by generating a charge by the irradiation with radioactive rays to carry the radiation image and storing the generated charge, and also, that reads the stored charge generated by the irradiation with reading light; a surface light source where many linear light emitters for emitting the reading light are arrayed; and a detecting part having an integral amplifier for integrating the charge flowing out of the radiation image detector, wherein the radiation image is read while successively switching the light emission among many linear light emitters. <P>SOLUTION: The light emission of the linear light emitter is controlled so that the light emission may be switched among the linear light emitters during the integration period of the integral amplifier. <P>COPYRIGHT: (C)2008,JPO&INPIT

Description

  The present invention generates charges when irradiated with radiation carrying a radiation image, accumulates the charges and records a radiation image, generates charges when irradiated with reading light, and generates the charges. A radiation image recording / reading apparatus comprising a radiation image detector from which accumulated electric charges are read out and a planar light source in which a large number of linear light emitters for emitting reading light are arranged, the light emission of a large number of linear light emitters The present invention relates to a radiation image recording / reading apparatus that sequentially reads and reads out images.

  Conventionally, in the medical field and the like, various radiation image detectors that record radiation images related to a subject by receiving radiation that has passed through the subject and detect an image signal corresponding to the recorded radiation image have been proposed and put into practical use. ing.

  As the radiation image detector, for example, there is a radiation image detector using a semiconductor material that generates an electric charge when irradiated with radiation. For example, a so-called optical reading type is proposed as such a radiation image detector. ing.

  Examples of the optical reading type radiographic image detector include a first electrode layer that transmits radiation, a photoconductive layer for recording that generates charges when irradiated with radiation, and an insulator for latent image charges. A charge transport layer that acts as a conductor for transport charges having a polarity opposite to that of the latent image charge, a read photoconductive layer that generates charges when irradiated with read light, and transmits the read light There has been proposed a radiation image detector in which second electrode layers in which linear electrodes to be arranged are arranged in parallel are laminated in this order.

  A radiation image recording / reading apparatus that records and reads a radiation image using the above-described radiation image detector has been proposed. In the radiation image recording / reading apparatus, first, the first electrode layer and the first electrode layer In a state where a voltage is applied between the two electrode layers, radiation is emitted from the radiation source toward the subject, and the radiation that has passed through the subject is emitted from the first electrode layer side of the radiation image detector, The recording photoconductive layer is irradiated through the first electrode layer. Then, charge pairs are generated by irradiation of radiation in the recording photoconductive layer, and one of the polar charges is combined with the charge charged in the first electrode layer and disappears, and the other charge is latent image charge. As a result, a radiation image is recorded by being accumulated in a power storage unit formed at the interface between the recording photoconductive layer and the charge transport layer.

  When reading a radiographic image, linear reading light emitted from a reading light source is irradiated from the second electrode layer side, and the reading light passes through the linear electrode and reaches the reading photoconductive layer. As a result of the irradiation of the reading light, a charge pair is generated in the reading photoconductive layer, and the charge of one polarity of the charge pair is combined with the latent image charge in the power storage unit, and the charge of the other polarity is the first charge. The linear electrode of the second electrode layer is combined with the charged electric charge. Then, as described above, the electric charge of the other polarity is combined with the electric charge charged on the linear electrode of the second electrode layer, whereby a current flows through the linear electrode, and this current is connected to each linear electrode. The image signal is detected by the amplifier and the radiation image is read.

  As a reading light source used in the radiation image recording / reading apparatus as described above, for example, a planar light source using an organic EL has been proposed. For example, in Patent Document 1, Patent Document 2, and Patent Document 3, A radiation image recording / reading apparatus in which the radiation image detector and the planar light source are integrally laminated has been proposed. The planar light source in the radiation image recording / reading apparatus includes a planar electrode, a light emitting layer that emits reading light, and a plurality of reading light beams that extend in a direction perpendicular to the length direction of the linear electrode in the radiation image detector. A linear electrode layer having a plurality of linear electrodes is laminated, and reading light emitted from the light emitting layer is applied by applying a voltage between the planar electrode and each linear electrode in the linear electrode layer. The radiation image detector is transmitted through the linear electrode, and the radiation image detector can be scanned with the linear reading light by sequentially switching the voltage application for each linear electrode.

JP 2000-162726 A JP 2001-27697 A JP 2001-26496 A

  However, when the voltage applied to each linear electrode of the planar light source is sequentially switched as described above, the linear electrode of the planar light source and the linear electrode of the radiation image detector are capacitively coupled, and the line of the planar light source The voltage fluctuation of the electrode has an effect on the linear electrode of the radiation image detector and is detected as a noise signal.

  In view of the above circumstances, the present invention provides a radiographic image recording / reading apparatus in which the radiographic image detector and the planar light source as described above are integrated, and can suppress the noise signal as described above. The object is to provide an apparatus.

  The radiographic image recording / reading apparatus of the present invention generates a charge by receiving radiation carrying a radiographic image, records the radiographic image by accumulating the charge, and generates a charge by receiving reading light. A radiation image detector that reads out the accumulated charge by the generation of the charge, the radiation image detector comprising an electrode layer in which a large number of linear electrodes for reading the accumulated charge are arranged; A planar light source extending in a direction orthogonal to the linear electrode, and a plurality of linear light emitters for emitting reading light arranged in the extending direction of the linear electrode, and an integrating amplifier for integrating the electric charge flowing out of the linear electrode A radiation image recording / reading apparatus including a detection unit having a plurality of linear light emitters, wherein the light emission of the linear light emitters is switched. There characterized by comprising a light emission control unit for controlling light emission of the linear light-emitting body such that during the integration period of the integration amplifier.

  In the radiographic image recording / reading apparatus of the present invention, the light emission control unit may control the linear light emitter so that the switching of the light emission of the linear light emitter is the integration start time of the integration amplifier. it can.

  Further, the detection unit shall perform correlated double sampling, and the light emission control unit shall control the linear light emitter so that the switching of the light emission of the linear light emitter is the signal component acquisition start time. it can.

  Further, the detection unit performs correlated double sampling, and the light emission control unit sets the linear light emitter so that the switching of light emission of the linear light emitter is at the time when the baseline sampling time has elapsed from the end of the baseline sampling. Can be controlled.

  Further, the planar light source may be provided with a plate electrode, and a smoothing capacitor may be provided on the plate electrode.

  Further, the planar light source may be provided with a flat plate electrode, and may be provided with a current source for supplying a dummy current to the flat plate electrode.

  Further, it is possible to prevent the electric charge read out by the light emission of the linear light emitter in the leading line from being acquired as an image signal.

  According to the radiation image recording / reading apparatus of the present invention, since the light emission of the linear light emitter is controlled so that the light emission of the linear light emitter is switched during the integration period of the integration amplifier, The noise signal that is generated when the light emitter is turned off from the on state and the noise signal that is generated when the linear light emitter of the next line is turned on from the off state can be canceled with each other. Noise signal can be suppressed.

  Hereinafter, an embodiment of a radiation image recording / reading apparatus of the present invention will be described with reference to the drawings. FIG. 1 is a perspective view showing a schematic configuration of the radiation image recording / reading apparatus.

  As shown in FIG. 1, this radiographic image recording / reading apparatus generates a charge upon irradiation with radiation carrying a radiographic image, records the radiographic image by accumulating the charge, and irradiates with reading light. A radiation image detector 10 that generates a charge upon receipt of the charge and outputs a charge signal corresponding to the amount of the accumulated charge, and a planar light source that emits reading light L toward the radiation image detector 10 20.

  In detail, as shown in FIG. 1, the radiation image detector 10 receives the radiation of the first electrode layer 11 that transmits the radiation carrying the radiation image and the radiation that has passed through the first electrode layer 11. The recording photoconductive layer 12 that generates charges, the charge that acts as an insulator for the charges generated in the recording photoconductive layer 12, and the charge that acts as a conductor for transport charges of the opposite polarity to the charges A transport layer 13, a photoconductive layer for reading 14 that generates charges when irradiated with the reading light L, and a second electrode in which a large number of linear electrodes 15a that extend linearly that transmit the reading light are arranged in parallel The layer 15 is laminated on the glass substrate 16. A power storage unit 17 is formed at the interface between the recording photoconductive layer 12 and the charge transport layer 13 in which charges generated according to the radiation dose are stored.

  The first electrode layer 11 is a planar electrode and is formed of, for example, a material such as Au, but may be formed of any material as long as it is a material that transmits radiation.

  The recording photoconductive layer 12 only needs to generate a charge when irradiated with radiation, and is excellent in that it has a relatively high quantum efficiency with respect to radiation and a high dark resistance. A material mainly composed of Se is used. A thickness of about 10 μm is appropriate.

Charge as the transport layer 13, for example, the mobility of the charge charged on the first electrode layer 11 may greater the difference in mobility of the charge and vice versa polarity (e.g. 10 ² or more, preferably 10 ³ or more ) PVK (Poly (N-vinylcarbazole)), TPD (N, N'-diphenyl-n, n'-bis (3-methylphenyl) -1,1'-biphenyl-4,4'-diamine) and discotic liquid crystal An organic compound such as TPD polymer (polycarbonate, polystyrene, PVK) dispersion, or a semiconductor material such as a-Se doped with 10 to 200 ppm of Cl is suitable.

  The reading photoconductive layer 14 may be any material that exhibits conductivity when irradiated with the reading light L. For example, a-Se, Se-Te, Se-As-Te, metal-free phthalocyanine, metal phthalocyanine A photoconductive substance mainly composed of at least one of MgPc (Magnesium phtalocyanine), VoPc (Phase II of Vanadyl phthalocyanine), CuPc (Cupper phtalocyanine), and the like is preferable. A thickness of about 0.1 to 1 μm is appropriate.

  The second electrode layer 15 is composed of a large number of linear electrodes 15a as described above, and any material may be used as long as it can transmit the reading light emitted from the planar light source 20. For example, ITO or IZO can be used. The thickness is suitably about 0.2 μm. Further, Al, Au, or the like can be used as a thickness that allows the reading light L to pass therethrough.

  In the radiographic image recording / reading apparatus of the present embodiment, a so-called direct conversion type radiographic image detector 10 is used. However, the so-called indirect conversion type that emits fluorescence upon irradiation with radiation and photoelectrically converts the fluorescence. The radiation image detector may be used.

  The planar light source 20 is obtained by laminating a cathode layer 21, a light emitting unit layer 22 and an anode layer 23 on a glass substrate 24.

  The cathode layer 21 is composed of a large number of linear electrodes 21a arranged in parallel, and the linear electrodes 21a are formed of a conductor such as aluminum, for example.

  The anode layer 23 is composed of a light-transmitting conductive layer such as an ITO film, and is formed on the glass substrate 24 in a planar shape.

  As shown in FIG. 2, the light emitting unit layer 22 is formed by alternately laminating light emitting layers 25 that emit reading light L and layers 25a that form equipotential surfaces (hereinafter referred to as “CGL” (Charge Generation Layer)). Is.

  The planar light source 20 is constituted by a so-called multi-photon emission element as described above. The planar light source 20 is not limited to the layer configuration as described above, and for example, a laminated structure of an anode layer, a hole transport layer, a light emitting layer, and a cathode layer, an anode layer, a hole transport layer, a light emitting layer, and an electron transport layer. And a cathode layer, a cathode layer, an anode layer, a hole transport layer, a light emitting layer, an electron transport layer, an electron injection layer, and a cathode layer.

  The anode layer 23 and each linear electrode 21a of the cathode layer 21 are electrically connected to the light emission control unit 40. The light emission control unit 40 is connected to the anode layer 23 and each linear electrode 21a with a light emitting unit layer. A driving voltage for causing the reading light to be emitted from 22 is applied. Further, the light emission control unit 40 and each linear electrode 21a are connected via a switch element 31, and when the switch element 31 connected to each linear electrode 21a is sequentially turned on, the linear electrode 21a is sequentially turned on. A driving voltage is applied, and thereby linear reading light L is emitted sequentially.

  As shown in FIG. 1, the radiation image detector 10 and the planar light source 20 are arranged so that the linear electrode 15a in the radiation image detector 10 and the linear electrode 21a of the planar light source 20 are orthogonal to each other. As described above, when the switch elements 31 are sequentially turned on, the linear reading light L is scanned in the length direction of the linear electrodes 15a of the radiation image detector 10.

  Further, as shown in FIG. 3, each linear electrode 15 a of the radiation image detector 10 is provided with a detection unit 50.

  The detecting unit 50 integrates the charge signal output from the radiation image detector 10, the first and second holding circuits 32 and 53 that hold the electric signal integrated by the integrating amplifier 51, the first and second holding circuits A differential amplifier 54 that outputs a difference between the first electric signal and the second electric signal held in the second holding circuits 52 and 53, respectively, and an analog signal that is output from the differential amplifier 54 is converted to a digital signal. A / D converter 55 is provided to perform correlated double sampling processing based on the charge signal output from the radiation image detector 10.

  The integrating amplifier 51 includes a capacitor 51a for accumulating the charge signal output from the radiation image detector 10 and a reset switch S1 for discharging the charge signal accumulated in the capacitor 51a.

  The first holding circuit 52 includes a switch S2 and a capacitor C1, and holds the electric signal output from the integrating amplifier 51 in the capacitor C1.

  The second holding circuit 53 includes a switch S3 and a capacitor C2, and holds the electric signal output from the integrating amplifier 51 in the capacitor C2.

  The detection unit 50 also includes buffer amplifiers 56 and 57 that output the electrical signals output from the first and second holding circuits 52 and 53 to the differential amplifier 34, a reset switch S1 of the integration amplifier 51, the first and first amplifiers. And a control circuit 58 for controlling the operation timing of the switches S2 and S3 of the second holding circuits 52 and 53, the A / D converter 35, and the like.

  Next, the operation of recording and reading a radiographic image in the radiographic image recording / reading apparatus will be described with reference to FIG. In FIG. 4, the glass substrate 16 in the radiation image detector 10 is not shown.

  First, the first electrode layer 11 and the second electrode layer are so charged that the first electrode layer 11 of the radiation image detector 10 is negatively charged and the linear electrode 15a of the second electrode layer 15 is positively charged. A voltage is applied between In the state where the voltage is applied as described above, the radiation R is emitted toward the subject 60 from a radiation source (not shown). As shown in FIG. 4A, the radiation R emitted from the radiation source is applied to the entire subject 60, and the radiation that has passed through the portion 60 a that transmits the radiation of the subject 60 is the first of the radiation image detector 10. Irradiation from the electrode layer 11 side. Note that the radiation irradiated to the portion 60 b that does not transmit radiation in the subject 60 is not irradiated to the radiation image detector 10.

  The radiation R applied to the radiation image detector 10 passes through the first electrode layer 11 and is applied to the recording photoconductive layer 12. Then, a charge pair is generated by irradiation of radiation in the recording photoconductive layer 12, and the positive charge is combined with the negative charge charged in the first electrode layer 11 and disappears, and the negative charge is a latent image charge. Are stored in the power storage unit 17 formed at the interface between the recording photoconductive layer 12 and the charge transport layer 13, and a radiation image is recorded.

  Then, after the radiographic image is recorded as described above, the radiographic image is read. When reading a radiographic image, first, the first electrode layer 11 of the radiographic image detector 10 is grounded, the switch elements 31 in the planar light source 20 are sequentially switched, and the light emission control unit 40 shown in FIG. A driving voltage is sequentially applied to the electrode 21a. Then, the linear reading light L is emitted from the light emitting unit layer 22 by the application of the driving voltage to each linear electrode 21 a as described above, and the linear reading light L is irradiated to the radiation image detector 10.

  Then, the linear reading light L irradiated from the second electrode layer 15 side as described above passes through the linear electrode 15a and is irradiated to the reading photoconductive layer 14, and by this reading light L irradiation, Charge pairs are generated in the reading photoconductive layer 14, and positive charges of the charge pairs are combined with latent image charges in the power storage unit 17, and negative charges are applied to the linear electrodes 15 a of the second electrode layer 15. Combines with a charged positive charge.

  Then, as described above, the negative charge is combined with the positive charge charged on the linear electrode 15a of the second electrode layer 15, whereby a current flows through the linear electrode 15a, and this current is connected to each linear electrode 15a. The detection unit 50 detects the image signal.

  An image signal is detected by the detection unit 50 for each irradiation of one line of the linear reading light L as described above, and an image signal for each pixel constituting the radiation image is acquired. Then, by scanning the entire surface of the radiation image detector 10 with the linear reading light L, an image signal for each pixel of the entire radiation image is acquired.

  Here, the irradiation timing of the reading light L and the timing of the correlated double sampling of the detection unit 50 when reading is performed as described above will be described with reference to the timing chart of FIG.

  When reading is performed as described above, first, the reset switch S1 of the integration amplifier 51 in the detection unit 50 is turned off, and integration of the charge signal is started in the integration amplifier 51 from the time t0 shown in FIG. The

  At the integration start time t0 in the integrating amplifier 51, the switch S2 of the first holding circuit 52 is turned on, and the electric signal integrated by the integrating amplifier 51 is accumulated in the capacitor C1 of the first holding circuit 32. The

Then, after the integration by the integrating amplifier 51 is started, the switch S2 of the first holding circuit 52 is turned off at the time t1 when a predetermined baseline sampling time _tbase has elapsed, and the first accumulated in the capacitor C1. 1 electrical signal is held.

  Then, at the time point t1 when the first electric signal is held by the capacitor C1 as described above, the switch S3 of the second holding circuit 53 is turned on. That is, the electrical signal output from the integrating amplifier 51 from this time is stored in the capacitor C2 of the second holding circuit 53. At this time, the switch element 31 connected to the linear electrode 21a of the leading line (line 1) in the planar light source 20 is turned on, and linear reading is performed from a position corresponding to the linear electrode 21a of the line 1. Light L is emitted and applied to the radiation image detector 10.

  Then, at a time point t2 when a predetermined sampling time has elapsed, the reset switch S1 is turned on, the integrating amplifier 51 is reset, and the switch S3 of the second holding circuit 53 is turned off and stored in the capacitor C2. The second electric signal (the signal component in the claims) is held.

  Then, the first electric signal held in the capacitor C1 of the first holding circuit 52 and the second electric signal held in the second holding circuit 53 as described above are supplied to the buffer amplifiers 56 and 57, respectively. To the differential amplifier 54. Then, the differential amplifier 54 calculates the difference between the two electric signals and outputs the difference to the A / D converter 55. The A / D converter 55 digitally converts the difference signal, which is an input analog image signal, and outputs a digital image signal.

  Then, at the time t3 when the A / D conversion is completed as described above, the reset switch S1 of the integration amplifier is turned off again, and the integration in the integration amplifier 51 is started again.

Then, after the integration by the integrating amplifier 51 is started, the switch S2 of the first holding circuit 52 is turned off at a time t4 when a predetermined baseline sampling time _tbase has elapsed, and the first accumulated in the capacitor C1 is stored. 1 electrical signal is held.

  At time t4 when the first electric signal is held by the capacitor C1 as described above, the switch S3 of the second holding circuit 53 is turned on, and the electric signal output from the integrating amplifier 51 from this time is the first signal. 2 is stored in the capacitor C2 of the second holding circuit 53. At this time, the switch element connected to the line electrode 21a of the line 1 in the planar light source 20 is turned off, and the switch element 31 connected to the line electrode 21a of the next line (line 2). Is turned on, and the linear reading light L is emitted from the portion of the line 2 corresponding to the linear electrode 21a, and is applied to the radiation image detector 10.

  At a time point t5 when a predetermined sampling time has elapsed, the reset switch S1 is turned on, the integrating amplifier 51 is reset, and the switch S3 of the second holding circuit 53 is turned off and stored in the capacitor C2. The second electric signal is held.

  Then, the first electric signal held in the capacitor C1 of the first holding circuit 52 and the second electric signal held in the second holding circuit 53 as described above are supplied to the buffer amplifiers 56 and 57, respectively. To the differential amplifier 54. Then, the differential amplifier 54 calculates the difference between the two electric signals and outputs the difference to the A / D converter 55. The A / D converter 55 digitally converts the difference signal, which is an input analog image signal, and outputs a digital image signal.

  Then, at the time t6 when the A / D conversion is completed as described above, the integration amplifier switch S1 is turned off again, and the integration in the integration amplifier 51 is started again.

Then, after the integration by the integration amplifier 51 is started, the switch S2 of the first holding circuit 52 is turned off at a time t7 when a predetermined baseline sampling time _tbase elapses, and the first accumulated in the capacitor C1. 1 electrical signal is held.

  At time t7 when the first electric signal is held by the capacitor C1 as described above, the switch S3 of the second holding circuit 53 is turned on, and the electric signal output from the integrating amplifier 51 from this point is 2 is stored in the capacitor C2 of the second holding circuit 53. At this time, the switch element connected to the linear electrode 21a of the line 2 in the planar light source 20 is turned off and connected to the linear electrode 21a of the next line (line 3) of the line 2. The switch element 31 is turned on, and the linear reading light L is emitted from a portion corresponding to the linear electrode 21 a of the line 3 and irradiated to the radiation image detector 10.

  Thereafter, similarly to the above, when a predetermined sampling time has elapsed, the reset switch S1 is turned on, the integrating amplifier 51 is reset, and the switch S3 of the second holding circuit 53 is turned off. The second electric signal stored in the capacitor C2 is held.

  Then, the first electric signal held in the capacitor C1 of the first holding circuit 52 and the second electric signal held in the second holding circuit 53 as described above are supplied to the buffer amplifiers 56 and 57, respectively. To the differential amplifier 54. Then, the differential amplifier 54 calculates the difference between the two electric signals and outputs the difference to the A / D converter 55. The A / D converter 55 digitally converts the difference signal, which is an input analog image signal, and outputs a digital image signal.

  Thereafter, in the same manner as described above, the timing of S1 to S3 is controlled, and the on / off timing of the switch element 31 of the planar light source 20 is controlled, and each time one line of reading light is irradiated. A digital image signal for one line is detected. Finally, digital image signals for the entire surface of the radiation image detector 10 are detected.

  Here, FIG. 5 shows a noise signal flowing through the linear electrode 15a of the radiation image detector 10 when the linear electrode 21a of the planar light source 20 is sequentially switched as described above. As shown in FIG. 5, the noise signal is generated by turning off the switch element connected to the line electrode 21a of the line 1, and the switch element connected to the line electrode 21a of the line 2 is turned on. Occurs by making a state. In the radiographic image recording / reading apparatus according to the present embodiment, as shown in FIG. 5, the switching from the line 1 to the line 2 is performed during the integration period by the integration amplifier 51. The noise signal generated by turning off the switch element connected to 21a and the noise signal generated by turning on the switch element connected to the linear electrode 21a of line 2 are mutually canceled, Noise signal can be suppressed. Similarly, the switching from the line 2 to the line 3 is performed during the integration period by the integration amplifier 51, so that the switching element connected to the linear electrode 21a of the line 2 is turned off. The noise signal and the noise signal generated by turning on the switch element connected to the linear electrode 21a of the line 3 are canceled each other, and the noise signal can be suppressed.

  In the above embodiment, the switching of the reading light for each line of the planar light source 20 is performed at the time of obtaining the second electric signal. However, the present invention is not limited to this, for example, as shown in FIG. Switching may be performed when the baseline sampling time has elapsed since the end of the baseline sampling. That is, switching may be performed at the timings t1 ', t4', and t7 'shown in FIG. When the reading light is switched at the timing shown in FIG. 5, for example, the reading light of line 1 is irradiated until the baseline sampling time of the next line, so that the charge generated by the irradiation of the reading light of line 1 is This is added to the charge signal of the baseline sampling of the next line, and the first electric signal is increased accordingly. Therefore, as shown in FIG. 6, by extending the irradiation of the reading light of the previous line to the time when the baseline sampling time has elapsed from the end of the baseline sampling, the charge generated by the irradiation of the previous line is changed to the number of the next line. Since it can be added not only to the first electric signal but also to the second electric signal, a more appropriate image signal can be obtained.

  Further, a smoothing capacitor may be provided on the anode layer 23 of the planar light source 20. By providing the smoothing capacitor as described above, the noise signal can be smoothed.

  Further, a current source is provided in the anode layer 23 of the planar light source 30 so that, for example, a dummy current is passed through the anode layer 23 when reading the first line and / or reading the last line. Good. For the first line, the noise signal generated at the start of reading light irradiation cannot be removed by switching the reading light as described above, but the noise signal is removed by flowing a dummy current as described above. be able to. In addition, for the last line, the noise signal generated when reading light irradiation is stopped cannot be removed by switching the reading light as described above, but the noise signal is generated by flowing a dummy current as described above. Can be removed.

  Further, since the noise signal generated by the irradiation of the reading light of the first line cannot be canceled, the image signal read by the irradiation of the reading light of the first line may not be acquired.

The figure which shows schematic structure of the radiographic image detector and planar light source in the radiographic image recording and reading apparatus of this invention Sectional drawing which shows schematic structure of planar light source Diagram showing the configuration of the detector The figure for demonstrating the effect | action of recording and reading of the radiographic image by the radiographic image recording and reading apparatus shown in FIG. The figure which shows the irradiation timing of reading light, and the timing of the correlation double sampling of a detection part The figure which shows the irradiation timing of reading light, and the timing of the correlation double sampling of a detection part

Explanation of symbols

DESCRIPTION OF SYMBOLS 10 Radiation image detector 11 1st electrode layer 12 Recording photoconductive layer 13 Charge transport layer 14 Photoconductive layer for reading 15 2nd electrode layer 16 Glass substrate 20 Planar light source 21 Cathode layer 22 Light emitting unit layer 23 Anode layer 24 Glass substrate 50 Detector 51 Integrating amplifier 60 Subject

Claims (6)

A charge is generated upon irradiation with radiation carrying a radiation image, and the radiation image is recorded by accumulating the charge, and a charge is generated upon irradiation with reading light, and the accumulation is performed by the generation of the charge. A radiation image detector for reading out the stored charge, the radiation image detector having an electrode layer in which a plurality of linear electrodes for reading out the accumulated charge are arranged, and a direction orthogonal to the linear electrode A planar light source in which a plurality of linear light emitters that emit the reading light are arranged in a direction in which the linear electrodes extend, and a detection unit that includes an integration amplifier that integrates the electric charge flowing out to the linear electrodes. In the radiation image recording / reading apparatus, the radiation image recording / reading apparatus that sequentially reads out the light emitted from the plurality of linear light emitters,
A radiation image recording / reading apparatus comprising: a light emission control unit configured to control light emission of the linear light emitter so that light emission of the linear light emitter is switched during an integration period of the integration amplifier. The detection unit performs correlated double sampling;
2. The radiation image recording / reading according to claim 1, wherein the light emission control unit controls the linear light emitter so that the switching of the light emission of the linear light emitter is a signal component acquisition start time. apparatus. The detection unit performs correlated double sampling;
The light emission control unit is configured to control the linear light emitter so that the light emission of the linear light emitter is switched when the baseline sampling time elapses from the end of the baseline sampling. Item 2. The radiographic image recording / reading apparatus according to Item 1. The planar light source is provided with a plate electrode,
4. The radiographic image recording / reading apparatus according to claim 1, wherein a smoothing capacitor is provided on the flat plate electrode. The planar light source is provided with a plate electrode,
5. The radiographic image recording / reading apparatus according to claim 1, further comprising a current source for supplying a dummy current to the flat plate electrode.   6. The radiographic image recording / reading apparatus according to claim 1, wherein a charge read out by light emission of the linear light emitter in the leading line is not acquired as an image signal.

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