CN1317568C - Optical detecting device x-ray photographic method and apparatus and photo-electric conversion components - Google Patents
Optical detecting device x-ray photographic method and apparatus and photo-electric conversion components Download PDFInfo
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- CN1317568C CN1317568C CNB031382894A CN03138289A CN1317568C CN 1317568 C CN1317568 C CN 1317568C CN B031382894 A CNB031382894 A CN B031382894A CN 03138289 A CN03138289 A CN 03138289A CN 1317568 C CN1317568 C CN 1317568C
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Abstract
An X-ray sensing apparatus with which reduction is achieved in the amount of electric power consumed to drive an X-ray sensor, including: a sensing unit including a plurality of photoelectric conversion elements each converting light into an electric signal; a driving range designating unit for designating a driving range for driving each of the plurality of photoelectric conversion elements included in the sensing unit; a drive unit for driving the photoelectric conversion element in the driving range designated by the driving range designating unit; a reading range designating unit for designating a reading range of the photoelectric conversion element driven by said driving unit; and a signal reading unit for reading out an output of the photoelectric conversion element in the reading range designated by the reading range designating unit.
Description
Technical field
The present invention relates to control X ray method for imaging, X ray camera and the components of photo-electric conversion of the driving of the components of photo-electric conversion, particularly relate to the driving scope of having considered the components of photo-electric conversion and X ray method for imaging, X ray camera and the components of photo-electric conversion of read range.
Background technology
In X ray camera in the past, shine X-ray beam from x-ray source by the such analyzed object of medical patient, after X-ray beam has passed through detected body, use the panel film loader, the film Auto-changer, CR (Computed Radiography), FPD (Flat Panel Detector) etc. photographs.
Propose to have used the high-resolution solid X-ray detector of FPD in X-ray radiography, this detecting device has by the X ray sensor that has used 3000～4000 to constitute as the two-dimensional array of the components of photo-electric conversion of representative with photodiode etc. in each dimension.Each components of photo-electric conversion generate and the corresponding electric signal of amount that projects the X ray on the X ray sensor.Thus, subject is placed between x-ray source and the X ray sensor, the X ray quantitative change that has seen through subject is changed to electric signal, obtain the X ray picture of subject.In addition, read laggard capable digitizing respectively, carry out Flame Image Process, storage and demonstration then from the signal of each components of photo-electric conversion.Such detecting device for example is disclosed in the Japanese Patent Application Publication spy and opens in the flat 9-257944 communique.
And then, be accompanied by the raising of slimming, high reliability technology, used the solid X-ray detector of FPD also as X ray panel film loader, realizing miniaturization, slimming.
But, in having used the solid X-ray detector of FPD, have the such problem of a large amount of power of consumption aspect the driving of the components of photo-electric conversion in X ray sensor.Particularly, for example loaded under the situation of battery the driving of the power that the slim X ray camera in the time of need reducing common photography is consumed in slim, small-sized X ray digital photographic device inside.
Summary of the invention
The object of the present invention is to provide the X ray camera and the X ray method for imaging of the driving of the X ray sensor that can save power, and the components of photo-electric conversion.
To achieve these goals, the invention provides a kind of components of photo-electric conversion, comprising: the optical detection device that light is transformed to electric signal; Amplification is by the multiplying arrangement of the electric signal of this optical detection device output; The driving of this multiplying arrangement is carried out the drive unit of ON/OFF control.
In addition, the invention provides a kind of X ray camera, comprising: by being used for that radioactive ray are transformed to the camera head that a plurality of components of photo-electric conversion of electric signal constitute; A plurality of multiplying arrangements that electric signal from above-mentioned a plurality of components of photo-electric conversion output is amplified; The driving of above-mentioned multiplying arrangement is carried out the drive unit of ON/OFF control.
In addition, the invention provides a kind of X ray camera, comprising: by being used for that light is transformed to the camera head that a plurality of components of photo-electric conversion of electric signal constitute; Be used to specify the driving scope specified device of the scope that each components of photo-electric conversion that constitute above-mentioned camera head are driven; The drive unit that the components of photo-electric conversion by the scope of above-mentioned driving scope specified device appointment are driven; And the signal reader that reads the output of the components of photo-electric conversion that driven by above-mentioned drive unit; Wherein, above-mentioned driving scope specified device is specified the scope that drives the above-mentioned components of photo-electric conversion by accompanying the coordinate entering device of above-mentioned camera head.
Other purposes of the present invention, feature and advantage, detailed description can be come to understand in conjunction with the drawings.In these accompanying drawings, identical represents same or analogous part with reference to label.
Description of drawings
Fig. 1 is the structural drawing of X ray camera chain.
Fig. 2 is the equivalent circuit diagram of the components of photo-electric conversion.
Fig. 3 shows the structure example of camera.
Fig. 4 is the structure example of the display device of operation X ray camera.
Fig. 5 is the structural drawing when specifying radioscopic image photography zone with the aperture concerted action.
Fig. 6 represents to specify with the aperture concerted action computing method of the device in radioscopic image photography zone.
Fig. 7 is the structural drawing when specifying radioscopic image photography zone by the device that is attached to the X ray camera.
Fig. 8 is the device that the exposure field recognition device during by a preceding shot is specified radioscopic image photography zone.
Fig. 9 is used to illustrate by using the relative position information between subject and the X ray camera, specifies the method in radioscopic image photography zone.
Figure 10 is the synoptic diagram by the power saving effect of the present invention's generation.
Figure 11 is the process flow diagram that the flow process in photography zone is selected in expression.
Embodiment
Preferred embodiments of the present invention will be described in detail with reference to the accompanying drawings.
The 1st embodiment
Below, with reference to accompanying drawing, explain embodiments of the invention 1.Fig. 1 illustrates the structured flowchart of the X ray camera chain of expression one embodiment of the invention.The 10th, X-ray room, the 12nd, X ray pulpit, the 14th, diagnosis room and other operation room.
In X ray pulpit 12, disposing the system controller 20 of controlling the total body action of this X ray camera chain.By X ray exposure request SW, touch-screen, mouse, keyboard, the operator interface 22 that operation room and foot-switch etc. constitute uses when the operator is input to system controller 20 to various instructions.Operator 21 instruction content for example has photography conditions (rest image/live image, x-ray tube voltage, tube current and x-ray bombardment time etc.), photography regularly, image capture conditions, the disposal route of those who are investigated ID and reading images etc., in addition, the establishing method that also has the photography zone, the affirmation in photography zone etc.
Photography control circuit 24 controls of system controller 20 are placed on the X ray camera chain in the X-ray room 10, and image processing circuit 26 carries out Flame Image Process to the image that the X ray camera chain by X-ray room 10 produces.Flame Image Process in the image processing circuit 26 for example is exposure field identification, the correction of view data, and spatial filtering, recurrence is handled, and tone is handled, scattered ray correction and dynamic range compression processing etc.The basic image data that memory storage 28 storage of high-capacity and high-speed has been handled by image processing circuit 26 for example is made of hard disk arrays such as (RAID).The 30th, the monitor scope of display image (being designated hereinafter simply as monitor), the 32nd, the control monitor 30 feasible display controllers that show various literal and image, the 34th, jumbo outer cryopreservation device (for example photomagneto disk), the 36th, the device that connects X ray pulpit 12 and diagnosis room or and the device of its operation room 14, the photographs in the X-ray room 10 etc. is sent to the LAN plate of the device of diagnosis room and other operation room 14.
In X-ray room 10, place the x ray generator 40 that X ray takes place.X ray generator 40 is by the X-ray tube 42 that X ray takes place, control the high-voltage power supply 44 that drives X-ray tube 42 by photography control circuit 24, and the X ray aperture 46 that the X-ray beam that is taken place by X-ray tube 42 is narrowed down in the desirable photography zone constitutes.The 47th, the CCD camera in the present embodiment, is provided with according to locating with the adjustment that the X-ray tube focus optically equates, constitutes by analyzing the photographs in the CCD camera 47, can monitor from the X ray of X-ray tube 42 radiation.
Have a medical check-up as patient tested and 50 to lie in photography with on the bed 48.Photography is driven according to the control signal from the control circuit 24 of photographing with bed 48, can change tested have a medical check-up for from the X-ray beam of x ray generator 40 towards.In photography below bed 48, configuration detection see through tested have a medical check-up 50 and photography with the X-ray detector 52 of the X-ray beam of bed 48.
The structure of the X-ray detector 52 in the key diagram 1.X-ray detector 52 is by grid 54, scintillater 56, X ray sensor (camera head) 58 that constitutes as the two-dimensional array of a plurality of components of photo-electric conversion and the laminated body that drives X ray exposure amount monitor device 60, and the driving circuit 62 of X ray sensor (camera head) 58 constitutes.Grid 54 is provided with in order to reduce by the influence that sees through the tested 50 X ray scatterings that produce of having a medical check-up.Grid 54 is made of low absorption piece of X ray and high absorption piece, and for example the Stripwise construction by Al and Pb constitutes.X-ray detector 52 makes grid 54 vibrations according to the setting from photography control circuit 24 when x-ray bombardment, and making can be because of the relation generation Moire fringe of X ray sensor (camera head) 58 with the grid ratio of grid 54.
Grid 54 vibrations are selected by the cameraman, grid 54 is fixedly photographed.Under the situation that grid 54 is fixedly photographed, preferably set for and be difficult to because of the Moire fringe that concerns generation aliasing or beat etc. of X ray sensor (camera head) 58 with grid 54 grids ratio.In addition, the grid striped itself is mirrored in the image, preferably also weakens the processing of the frequency etc. of grid striped itself by Flame Image Process.
In scintillater 56,, utilize it again in conjunction with the fluorescence of energy generation visible range by the parent material (absorption) of the high x-ray excitation fluorophor of energy.That is, X ray is transformed to visible light.This fluorescence has by parents such as CaWo4 or CdWo4 self and produces, and is perhaps produced by the luminescent center material in the parent that is added on CsI:Tl or ZnS:Ag.X ray sensor (camera head) 58 is transformed to electric signal to the visible light that is produced by scintillater 56.
In addition, in the present embodiment, scintillater 56 and X ray sensor (camera head) 58 are made independent structure, but also be applicable to by directly X ray being transformed in the X ray sensor (camera head) 58 that the components of photo-electric conversion of electronics constitute.For example, be the components of photo-electric conversion that constitute by the photographic department of armorphous Se or PbI2 etc. and non-crystalline silicon tft etc.
X ray exposure monitor 60 is to monitor that X ray transmission amount is that purpose disposes.Both can use the direct X ray that detect such as photo-sensitive cell of silicon metal as X ray exposure monitor 60, can also detect the fluorescence that produces by scintillater 56.In this embodiment, X ray exposure monitor 60 by in the substrate back film forming of X ray sensor (camera head) 58 the amorphous silicon photoreceptor element constitute, detect the visible light (proportional) of transmitted X-rays sensor (camera head) 58, its light amount information is sent to photography control circuit 24 with the X ray amount.Photography control circuit 24 is regulated the X ray amount according to the information Control high-voltage power supply 44 from X ray exposure monitor 60.Driving circuit 62 drives the components of photo-electric conversion that constitute photodetector array 58 under the control of photography control circuit 24, from each pixel read output signal.
Slim X-ray detector 152 in the key diagram 1.Slim X-ray detector 152 as the pictorial representation of multiple sensors 1, and also can exchange usage space resolution difference, the size of perhaps slim X-ray detector 152, the i.e. sensor that varies in size in photography zone etc.X-ray detector 52 with the difference of slim X-ray detector 152 is, the thickness of the first slim X-ray detector 152 is with below the corresponding to about 20mm of the box of film panel class, and this point is maximum difference.In addition, also be in slim X-ray detector 152, grid 54 is not installed in inside, simple and easy power supply and high capacity (more than 10 images below 20 images) storer has been installed in inside, can not have all points such as exchange that cable ground carries out picture signal and control signal with repeater 153.Equally, scintillater 56 is installed in inside, the laminated body of X ray sensor (camera head) 58 and driving X ray exposure monitor 60, and the driving circuit 62 of X ray sensor (camera head) 58.Can either there be cable 154 also can not have cable to move, under the situation of having used cable 154, transmits, so can realize the action that the image after the X ray photography is obtained, handles, confirmed the enough shorter time owing to can carry out image at high speed.This slim X-ray detector 152, for example for the four limbs etc. of photographing, other slim X-ray detector 152 is connected on the system controller 20 through repeater 153.
Diagnosis room in the key diagram 1 and other operation room 14.In diagnosis room and other operation room 14, being provided with to be connected is used for via the HIS/LIS of tested information of having a medical check-up of LAN plate indication photography and method for imaging etc. etc., image from LAN plate 36 is carried out the image processing terminal 70 of Flame Image Process, diagnosis supporting, the monitor 72 that the image (live image/rest image) from LAN plate 36 shows, image printer 74 and the file server 76 of preserving view data.
In addition, can be according to from the operator interface 22 in the X ray pulpit 12, the indication generation of image processing terminal 70 that perhaps is positioned at diagnosis room or other operation room 14 is from the signal for each equipment of system controller 20.
The elemental motion of system controller shown in Figure 1 20 is described.Driving governor 20 is according to operator 21 the indication photography control circuit 24 instruction photography conditions to the program of control X ray camera chain, photography control circuit 24 is according to this instruction, drive x ray generator 40, photography is taken the X ray picture with bed 48 and X-ray detector 52.Supply to image processing circuit 26 from the radioscopic image signal of X-ray detector 52 outputs, on monitor 30, carry out image after the Flame Image Process of implementation and operation person 21 appointments and show, simultaneously, be kept in the memory storage 28 as basic image data.Signal controller 20 is also according to operator 21 indication, and the image of carrying out once more Flame Image Process and result thereof shows, the transmission of the device of view data on network is preserved, image demonstration and film printing etc.
Elemental motion according to signal flow explanation system shown in Figure 1.The high-tension electricity potential source 44 of x ray generator 40 applies the high pressure that is used to take place X ray according to the control signal from photography control circuit 24 on X-ray tube 42.Thus, X-ray beam takes place in X-ray tube 42.The X-ray beam that taken place shines as patient tested through X ray aperture 46 and haves a medical check-up on 50.According to the position of the X-ray beam that will shine, by photography controller 24 control X ray apertures 46.That is, X ray aperture 46 is accompanied by the change in photography zone, X-ray beam is carried out shaping make and do not carry out unnecessary x-ray bombardment.
The X-ray beam of x ray generator 40 output among Fig. 1 see through lie in the radioparent photography of X ray with tested on the bed 48 have a medical check-up 50 and photography with beds 48, incide X-ray detector 52.In addition,, make with bed 48 by photography control circuit 24 control photography at tested 50 different parts or the direction transmitted X-rays bundle of having a medical check-up.In addition, using under the situation of slim X-ray detector 152, operator 21 regulates slim X-ray detectors 152 and testedly haves a medical check-up 50, makes that seeing through tested having a medical check-up from the X-ray beam of x ray generator 40 outputs 50 incides slim X-ray detector.At this moment,, be preferably in the not shown photography region appointment device of interpolation on the slim X-ray detector 152, make it possible to specify the zone that to photograph in order to limit the photography zone.In addition, can specify under the situation in X ray photography zone preestablishing, preferably make not shown photography zone display device be positioned at the surface of slim X-ray detector 152 grades with 46 concerted actions of X-ray tube aperture.
The grid 54 of the X-ray detector 52 among Fig. 1 reduces owing to the influence that sees through the tested 50 X ray scatterings that produce of having a medical check-up.Photography control circuit 24 makes grid 54 vibrations when x-ray bombardment, making can be because of the relation generation Moire fringe of photodetector array 58 with the grid ratio of grid 54.In scintillater 56, by the parent material (absorption X ray) of the high x-ray excitation fluorophor of energy, by at this moment take place again in conjunction with the fluorescence of energy generation visible range.The X ray sensor (camera head) 58 that disposes with scintillater 56 adjacency is the fluorescence conversions that take place in scintillater 56 electric signal.X ray exposure monitor 60 detects the visible light (proportional with the X ray amount) that has seen through X ray sensor (camera head) 58, and its detection limit information providing is arrived photography controller 24.Photography control circuit 24 blocks or regulates X ray according to this X ray exposure information Control high-voltage power supply 44.Driving circuit 62 drives X ray sensor (camera) 58 under the control of photography control circuit 24, read picture element signal from each photodetector.
The picture element signal of X-ray detector 52 from Fig. 1 and 152 outputs of slim X-ray detector outputs to the image processing circuit 26 in the X ray pulpit 12.Because it is big to be accompanied by the noise of X ray generation in X-ray room 10, therefore 26 signaling channel need be the high channel of noise immunity from X-ray detector 52 to image processing circuit, specifically, preferably adopt the digital transmission system of the error correction that possesses height, perhaps utilize the twisted-pair cable or the optical fiber of the band shielding of differential driver.
Image processing circuit 26 among Fig. 1 is according to the display format of switching picture signal from the instruction of system controller 20, and in addition, can also carry out the correction of picture signal in real time, spatial filtering processing and recurrence processing etc., can carry out tone and handle, scattered ray is proofreaied and correct and DR compresses processing etc.The image of having been handled by image processing circuit 26 shows on the picture of monitor 30.When realtime graphic was handled, the image information (primary image) of only having carried out image rectification was kept in the memory storage 28.In addition, according to operator 21 indication, the image information that is kept in the memory storage 28 constitutes feasible predetermined standard (for example, the Image Save ﹠amp that satisfies once more; Carry (IS ﹠amp; C)) after, be kept in the hard disk in outer cryopreservation device 34 and the file server 76 etc.
The device of the X ray pulpit 12 among Fig. 1 is connected to LAN (perhaps WAN) through LAN plate 36.On LAN, can connect a plurality of X ray camera chains certainly.LAN plate 36 is according to predetermined agreement (for example, Digital Imaging andCommunications in Medicine (DICOM)), output image data.On the picture that is connected to the monitor 72 on (perhaps WAN), radioscopic image is shown as static image of high resolving power and live image, when almost photographing, can realizes the real time remote diagnosis that the doctor carries out with X ray.
Fig. 2 represents an example as the equivalent electrical circuit of the components of photo-electric conversion of the component unit of X ray sensor (camera head) 58.1 components of photo-electric conversion is made of optical detecting unit 80 and the switching thin-film transistor (TFT) 82 of controlling charge storage and reading, and is general, formed by amorphous silicon (a-Si) on glass substrate.Optical detecting unit 80 also is made of the parallel circuit of optical diode 80a and capacitor 80b, writes the electric charge that the photoelectricity effect produces as constant current source 81.Capacitor 80b both can be the stray capacitance of optical diode 80a, also can be to improve the dynamic range of optical diode 80a and the capacitor that adds.The negative electrode of optical detecting unit (optical diode 80a) is connected on the bias supply 85 through the biasing wiring Lb as common electrode (D electrode).The anode of optical detecting unit 80 (optical diode 80a) is connected to capacitor 86 and electric charge from gate electrode (G electrode) through switching TFT 82 and reads with prime amplifier (multiplying arrangement) 88.The input of prime amplifier (multiplying arrangement) 88 also is connected to earth point through resetting with switch 90 and signal wire bias supply 91.In the present embodiment, in Fig. 2, adjust the power supply of prime amplifier (multiplying arrangement) 88,, adjust the power supply of the components of photo-electric conversion of the part that is designated as the photography zone perhaps according to control signal from the not shown driving circuit that carries out ON/OFF.By adjusting the power supply of prime amplifier (multiplying arrangement) 88, can suppress the power consumption of the components of photo-electric conversion.Particularly constituting with these components of photo-electric conversion under the situation of large-area X ray sensor (camera head) 58, adjusting the power supply of the components of photo-electric conversion in the unwanted scope of photography institute, the particular significant effect of inhibition power consumption.This is because use the components of photo-electric conversion of tens thousand of units in X ray sensor (camera head) 58.
Next uses Fig. 2 that the reading method of light-to-current inversion camera is described.Order among the figure roughly is divided into and resets, and three phases is read in storage.
Reset: temporarily making switching TFT 82 and resetting becomes conducting with switch 90, and 80b resets the electric capacity line.
Storage: then make switching TFT 82 and reset and turn-off with switch 90.Then, X ray taking place, is radiated at tested having a medical check-up on 50.Scintillater 56 looks like to be transformed to the luminous ray picture seeing through tested 50 the X ray of having a medical check-up, and optical diode 80a makes the charge discharge of capacitor 80b because this luminous ray looks like to become conducting state.
Read: make switching TFT 82 conductings, capacitor 80b is connected with capacitor 86.Thus, the information of the discharge capacity of capacitor 80b also is delivered to capacitor 86.By the voltage of prime amplifier (multiplying arrangement) 88 amplifications by the stored charge generation of capacitor 86, perhaps carry out electric charge-voltage transformation by the capacitor 89 that dots, output to the outside.
Light-to-current inversion when then, using Fig. 3 to illustrate the components of photo-electric conversion shown in Figure 2 are expanded to two dimension and constitute is moved.Fig. 3 is the equivalent electrical circuit of the X ray sensor (camera head) 58 that possesses the components of photo-electric conversion of two-dimensional arrangements.Because two dimension is read action with identical in above-mentioned two kinds of equivalent electrical circuit, so Fig. 3 uses equivalent electrical circuit shown in Figure 2 to realize.
X ray sensor among Fig. 3 (camera head) 58 is made of about 2000 * 2000～4000 * 4000 photovalve, and array area is about 200mm * 200mm～500mm * 500mm.The output of 1 components of photo-electric conversion is corresponding to 1 pixel.That is, in Fig. 2, X ray sensor (camera head) 58 is made of 4096 * 4096 pixel, and array area is 430mm * 430mm.Thus, the size of 1 pixel approximately is 105 * 105 μ m.4096 pixels that dispose along transverse direction as 1 piece, along 4096 pieces of longitudinal direction configuration, are made two-dimensional structure.
As Fig. 2 explanation, 1 components of photo-electric conversion is made of 1 optical detecting unit 80 and switching TFT 82.In Fig. 3, the components of photo-electric conversion (1,1)～(4096,4096) are shown, use switch SW (1,1)～(4096,4096) as the transmission of switching TFT.(m, (m n) is connected to for the common column signal line Lcm of these row gate electrode n) (G electrode) components of photo-electric conversion PD through corresponding switch SW.For example, components of photo-electric conversion PD (1,1)～(4096,1) of the 1st row are connected to the 1st column signal line Lc1.(m, common electrode n) (D electrode) all is connected to bias supply 85 through bias component Lb to each components of photo-electric conversion PD.
(m, control terminal n) are connected to common capable route selection Lrn with the switch SW of delegation.For example, switch SW (1,1)～(1,4096) of the 1st row is connected to capable route selection Lr1.Row route selection Lr1～4096 are connected to photography control circuit 24 through row selector (read range specified device) 92.Row selector (read range specified device) 92, by a control signal decoding from photography control circuit 24, decision will be read the address decoder 94 of signal charge of which the components of photo-electric conversion, and constitutes according to 4096 on-off element 96-1～96-4096 that the output of address decoder 94 opens and closes.According to this structure, can read the switch SW (m, the components of photo-electric conversion PD that n) is connected (m, signal charge n) that are connected on any capable Lrn.Can only carry out signal from the components of photo-electric conversion as target thus reads.
Row selector (read range specified device) 92 can be just be made of the shift register that uses in LCD etc. as the simplest structure.In the present embodiment, by select to take the zone of row with line decoder 94, has the effect of the time for reading that can shorten stored charge.This is in the on-the-spot effect that needs especially of the medical treatment that requires the demonstration in the short time.And then, using under the situation of X ray sensor (camera head) 58 aspect the live image, have the effect that improves frame rate.
Column signal line Lc1～4096 are connected to the signal read circuit 100 by 24 controls of photography control circuit.In signal read circuit 100,102-1～4096th resets and uses switch, respectively column signal line Lc1～4096 reset to the reference potential 101 that resets.106-1～4096 are respectively the prime amplifiers (multiplying arrangement) that amplifies from the signal potential of column signal line Lc1～4096,108-1～4096 are respectively that the sampling of the output of sampling maintenance prime amplifier 106-1～4096 keeps (S/H) circuit, the 110th, the output that sampling is kept (S/H) circuit 108-1～4096 multiplexing analog multiplexer on time shaft, the 112nd, digitized A/D transducer is exported in the simulation of traffic pilot 110.The output of A/D transducer 112 supplies to image processing circuit 26.In addition, by distinguish the power supply (not shown) of controlling and driving prime amplifier (multiplying arrangement) 106-1～4096 by the signal of photography control circuit 24 controls, can only drive the components of photo-electric conversion as target.In this structure, constitute the components of photo-electric conversion that are controlled at the column direction configuration, but also can constitute by controlling the driving of each components of photo-electric conversion respectively, adjust the driving of each components of photo-electric conversion.
In photodetector array shown in Figure 3,4096 * 4096 pixels are divided into 4096 row by column signal line Lc1～4096, read the signal charge of 4096 pixels of each row simultaneously, through each column signal line Lc1～4096, prime amplifier (multiplying arrangement) 106-1～4096 and S/H circuit 108-1～4096, be sent to analog multiplexer 110, it is multiplexing to carry out time shaft here, sequentially is transformed to digital signal by A/D transducer 112.That is, become the structure that reads signal according to every row, and, can also make the structure of reading of selecting the independent components of photo-electric conversion in each components of photo-electric conversion by switch 96-1～96-4096 is set.
In the present invention, the switch 98 of the power supply of the prime amplifier (multiplying arrangement) 88 by use adjusting each components of photo-electric conversion only makes the components of photo-electric conversion of camera coverage become ready state.This point by for supply power on the components of photo-electric conversion in photography zone only, and realizes with the power supply input of the prime amplifier (multiplying arrangement) 88 of the 106-1～106-4096 among not shown drive unit adjustment Fig. 3 in Fig. 3.This drive unit is accepted the control of photography control circuit 24.
In addition, in order to limit the camera coverage longitudinally of Fig. 3, row selector (read range specified device) 92 is the control signal decoding from photography control circuit 24, and the row of the signal charge of inverting element is read in 94 decisions through address decoder.Thus, open and close and be designated as the suitable on-off element of the scope of camera coverage (96-1～96-4096).
The 2nd embodiment
Fig. 4 represents to be specified by the device of operation X ray camera the display device in radioscopic image photography zone.Use Fig. 4, illustrate from the operating means of X ray camera and specify scope that drives the components of photo-electric conversion and the method for calling the output signal range of the components of photo-electric conversion.The 1101st, the example of display frame.As display device, use can be by with the direct display device of the touch-sensitive display imported of contact picture such as finger, pen.The 1102nd, that obtains image dwindles the summary image viewing area.Under the situation of having used slim X-ray detector 152, handle again by the image that the radio communication of utilizing the front sends, in this viewing area 1102, carry out image and show.The 1103rd, the button at demonstration and each X-ray detector 52 or slim X-ray detector 152 corresponding photography target positions is before photographing, by selector button 1103 specific photography targets.The 1104th, effective X-ray detector viewing area.In effective X-ray detector viewing area 1104, showing that expression is in the X-ray detector 52 under the system controller 20 may command states or the icon of slim X-ray detector 152.The 1105th, the image of CCD camera 47, the 1106th, the driving scope of the components of photo-electric conversion or the signal read range of the components of photo-electric conversion.Utilization is installed in the CCD camera on the X-ray tube, and process and the photography path of locating from the almost equal adjustment of the X ray of X-ray tube output mirror camera and quilt photography patient on image 1105.Image 1105 by on the touch-screen shown as the touch-screen of display device on finger or the driving scope of the pen indication components of photo-electric conversion or the signal read range 1106 of the components of photo-electric conversion, can specify the photography zone.
In this case, for example, indicate the preset coordinates (for example coordinate at four of X ray sensor angles) of the X ray sensor (camera head) 58 that shows in display frame 1105 in advance, the coordinate and the position on the X ray sensor (camera head) of calculating in advance and preserving on the display image 105 from indicated coordinate concern.Thus, photography control circuit 24 from touch-screen with the coordinate on the coordinate Calculation X ray sensor (camera head) 58 in the zone 1106 of finger or pen indication.
In addition, under the situation of the X ray sensor (camera head) 58 that has used embodiment 1,, determine the driving scope of the components of photo-electric conversion or the signal read range of the components of photo-electric conversion simultaneously by indicating area 1106.Like this, by using and the image that is adjusted the CCD camera 47 of location from the X ray of X-ray tube outgoing much at one, has the effect that to indicate the zone on the X ray sensor (camera head) 58 from display device 1101 simply.And then, on one side owing to can be in fact confirming on the display device 1101 that photography target indicates the zone on the X ray sensor (camera head) 58, so have the effect that can indicate needed minimal zone accurately.
Then, by pressing button 1103, the checked property information of selected photography target is read into the photography control circuit 24 from memory storage 28.Here, refer to physique, photography position, patient's sex, age, nationality, patient informations such as ethnic group as checked property information.At this moment, replace the checked property information distribution is arrived button 1103, also can in display frame 1101, add the project of input patient's checked property information.For example, make according to the patient information of physique etc. and roughly to determine employed photography zone, come roughly to determine the employed scope of photographing according to children and adult man.Thereby, if the driving scope of the components of photo-electric conversion on the X ray sensor (camera head) 58 or the signal read range of the components of photo-electric conversion then can be indicated in the center in the zone that indication hope is photographed on touch-screen.Adopting under the situation of this structure, having under the situation of the subject of same kind repeatedly being photographed etc., can indicate the effect in the zone that adapts with this subject.This is because if determined the kind of subject according to checked property information, then can add up ground or experience ground determine the to photograph cause in needed zone.
The 3rd embodiment
Fig. 5 is the knot figure that specifies the device in radioscopic image photography zone with the aperture concerted action, and Fig. 6 represents to specify with the aperture concerted action computing method of the device in radioscopic image photography zone.Concrete grammar when using Fig. 5, Fig. 6 that the aperture concerted action of the designation method of camera coverage and X-ray generator is described.
As shown in Figure 5, x ray generator 40 is by the X-ray tube 42 that X ray takes place, the control circuit 24 of being photographed is controlled and the high-voltage power supply 44 of driving X-ray tube 42, and the X ray aperture 46 that the X-ray beam that is taken place by X-ray tube 42 is narrowed down in the desirable photography zone constitutes.Here, the X ray aperture generally uses lead etc. in order to block X ray.X ray generator 40 possesses visible light sources 201 such as bulb in order to show the photography zone that is dwindled by X ray aperture 46.This visible light source 201 optically almost is equal to the focus 203 of X-ray tube 42 and the position relation of X ray aperture 46 with the position relation of X ray aperture 46.Thereby the scope of being shone by visible light 202 almost equates with the scope of irradiation X ray.
Embodiment when calculating its photography zone only is described according to the amount of this X-ray tube and X ray aperture and the geometric relationship of X ray camera.Needed information is distance (L1+L2) between X-ray tube-X ray camera when calculating the photography zone, distance (the Lx1 that leaves from the center of each collimation lens, Lx2, Ly1, Ly2), the central point of the X ray that takes place from X-ray tube arrived the positional information in the somewhere of X ray camera (SCx, SCy), inclination angle between X-ray tube and the X ray camera surface (θ x, θ y).
In addition, needed information when having set device has the distance L 1 from the X-ray tube focus to collimation lens.If according to these information, (Ssx1, Ssy1), (Ssx1, Ssy2), (Ssx2, Ssy1), (Ssx2, the Ssy2) scope of being surrounded then is calculated as the scope that X ray in the X ray camera is arrived as using
S sx1=SCx-(L1+L2) Lx1cos θ x/L1 (formula 1)
S sy1=SCy-(L1+L2) Ly1cos θ y/L1 (formula 2)
S sx2=SCx+ (L1+L2) Lx2cos θ x/L1 (formula 3)
S sy2=SCy+ (L1+L2) Ly2cos θ y/L1 (formula 4)
In addition, above-mentioned calculating hypothesis is rectangle or square by the scope that collimation lens defines the x-ray bombardment of scope, even and the scope ellipse or the circle that are defined the x-ray bombardment of scope by collimation lens also can be calculated the X ray scope of x-ray bombardment by same calculating.Wherein, the inclination angle between X-ray tube and the X ray camera surface (θ x, θ y) preferably is placed on catoptron the surface of X ray camera in advance, by utilizing the reflection by bulb irradiation, makes that θ x, θ y are 0 simultaneously.
Use comprises the above such scope of X ray camera coverage that obtains, the scope of coming definite power supply of going route selection or prime amplifier (multiplying arrangement) to drive.At this moment, select to make that by setting, can making the X ray camera coverage utilizes the scope bigger than x-ray bombardment scope, perhaps, utilize the structure of the scope littler than x-ray bombardment scope.Thus, measure necessary information in advance, then only measure the aperture amount of X-ray tube, just can determine the driving scope of X ray sensor or the effect of read range if having.
The 4th embodiment
Fig. 7 is the structure example of being specified radioscopic image photography zone by the device 210,211 that is attached to X ray sensor (camera head) 58.That is, explanation can be specified the driving scope of X ray sensor (camera head) 58 or the method for read range by the device 210,211 that is positioned at the X ray camera.Be positioned at the X ray camera appointment X ray camera coverage camera head auxiliary equipment 210,211 as shown in Figure 7, constitute and (for example be positioned at beyond the scope that to photograph, it is the neighboring area of camera head, the zone that does not have the components of photo-electric conversion), and this position be easy to the position that intuition is understood according to relation with radioscopic image photography zone.Among Fig. 7, have and the corresponding button 210 of each components of photo-electric conversion, wherein only light the employed components of photo-electric conversion as auxiliary equipment.The state of being lighted by LED etc. is the button 211 as auxiliary equipment.Can recall photography zone 212 from the button of lighting 211.This is because in this case, for example can determine the cause of camera coverage (for example 212 (A)) from the AND relation in length and breadth of the button 211 lighted.
But, for example,, as the zone of afterimage, associate 212 (C) sometimes, 212 (B) in that the photography zone is taken as under a plurality of situation such as 212 (A) and 212 (D).Thereby, under the situation in a plurality of zones of indication,, also can adopt a button 210 that is positioned at the horizontal axis of neighboring area is further segmented, the structure of the coordinate of expression vertical axis as with such shown in 215.
By pushing button 210 as auxiliary equipment, light button 211, indicate driving scope or read range on the X ray sensor (camera head) 58 simultaneously.Like this, analyze and definite driving scope or read range from the positional information photography control circuit 24 of button 211.In addition, as other structure, also can be constructed such that and adjust the switch 96 of row selector (read range specified device) 92, perhaps the not shown ON/OFF switch of the drive unit of the power supply of prime amplifier (multiplying arrangement) 88 input mechanically links.
The 5th embodiment
Fig. 8 be used to illustrate utilize before exposure field recognition device during a shot specify the method in radioscopic image photography zone.Use Fig. 8, the designation method of the X ray camera coverage of the exposure field information when having used a preceding shot is described.Directly use the exposure field scope of previous image, perhaps the information according to the exposure field scope of previous image has been moved driving scope or the read range (camera coverage) of the scope of preset distance as X ray sensor (camera head) 58.The identification of such exposure field for example can be opened among the 2000-271107 disclosed exposure field recognition methods and extracts by be implemented in the Japanese Patent Application Publication spy in image processing circuit 26.Photography control circuit 24 is according to the exposure field recognition result analysis of image processing circuit 26 and determine driving scope or read range.
Secondly, under the situation about having moved according to certain rule in known exposure field zone (photography zone), can coincide with the mobile phase in exposure field zone, photography control circuit 24 can sequentially be set driving scope or read range.For example, in the goods X-ray examination of airport, when the goods that is placed on the travelling belt is photographed when move in the photography zone of two dimensional surface radiation detecting apparatus, have power saving, short time and read such effect.
In addition, even also can be under the fixing situation in zone self, photography territory, when known subject self has moved according to certain rule, coincide with the mobile phase of subject, photography control circuit 24 is sequentially set the structure of driving scope or read range.In this case, when when move in photography zone, photographing, also have power saving, short time and read such effect.
Fig. 8 represent to photograph example of flow process.Use previous exposure field identifying information to carry out camera coverage when specifying, whether at first select can be with a preceding shot time identically, then, carry out whether can directly using the selection of the camera coverage that when a preceding shot, obtains.Under the situation of negating, by changing size, position, shape, the exposure field identifying information before can using during a shot, this point is favourable.In addition, so-called " previous " exposure field identifying information refers to image captured before the image that hope obtains, the image of not necessarily just having taken.
The 6th embodiment
When using sensor (camera head) 88 photographing moving pictures, the image of the subject that obtains from CCD camera 47, calculating is along with the time changes the poor of captured image, photography control circuit 24 calculate subjects generation the part that moves.Secondly, photography control circuit 24 only driving scope or the read range of the part that has taken place to move as sensor (camera head) 88, perhaps drives scope and read range.Thus, have and can shorten reading of image etc. in time, and the effect that reduces image volume.We can say just as the live image compression of having carried out hardware is handled.
The 7th embodiment
Fig. 9 is used to illustrate by using the relative position information between inspected object and the X ray camera, and the driving scope or the read range of indication sensor (camera head) 58 perhaps drive the method for scope and read range.Use Fig. 9, the method for using the relative position information between inspected object and the X ray camera is described.
About the relative position information between inspected object and the X ray camera, purpose is the camera coverage of understanding in the X ray camera, therefore do not need to understand three-dimensional positional information, preferably for example with the focus optical of X-ray tube on approaching position small-sized cameras such as CCD are set.
The 8th embodiment
Illustrate that decision used the method for X ray camera coverage of CCD camera 47.Image by the CCD camera is presented on the monitor, and the operator understood the X ray camera watched from the X ray dispensing device and the geometric relationship of subject before taking X ray.The operator at first specifies the scope of X ray camera with mouse etc., then specify in the scope of using in the photography with mouse etc.These information also can automatically be obtained by Flame Image Process.In addition, when automatically obtaining, also can use the photography position of appointment in the device of operation X ray camera by this Flame Image Process, patient's sex, at the age, sensor tube is apart from waiting camera coverage input information in addition.According to the scope of the X ray camera on the image of designated and selected CCD camera with wish the relative position relation of the scope of photography, can obtain the information of the employed amplifier components of photo-electric conversion etc.Because at this moment by using the inverse function of the position relation (formula (1)～formula (4)) on geometry illustrated in fig. 10, can know if make the aperture 10 of X ray dispensing device what change needed minimal X ray just can only externally take place, therefore can adopt the aperture 10 automatic structures that change that make the x ray generator device.
The scope in the expression photography zone of Fig. 9 is illuminated by bulb, obtains image by CCD camera 47 grades that are attached to X-ray tube, in order to specify in the position of the two dimensional surface sensor that uses in the photography, also can calculate by implementing Flame Image Process.
At this moment computation sequence below is described.First step: explore the radioscopic image camera by parameter recognition etc. from the CCD camera that is attached to X-ray tube.At this moment except the image of selecting from the CCD camera, for example, also can use X-ray tube-transducer spacing from, and incidental informations such as the kind of employed radioscopic image camera or size increase the rapidity and the correctness of calculating.In addition, remove automatically discern beyond, scope that can also be by the radioscopic image camera for example is shown on image and by the scope of the radioscopic image camera of visible illumination specifies in the scope of using in the photography.
Second step:, calculate the photography zone by find to have changed the scope of its hue information from the position of selected radioscopic image camera according to Flame Image Process by visible light.
Third step: the components of photo-electric conversion piece that uses when from 1. resulting photography zone and 2. the components of photo-electric conversion block message during radioscopic image camera arrival specifies in photography.
The 4th step: change parameter, make in control device, only to use and read at sky, read during photography, read the employed scope of each stage of photography such as the amplifier components of photo-electric conversion after the photography.
In addition, use under the situation of this two dimensional surface radiation detecting apparatus in live image etc., can only take a part sometimes, the part of other scope does not need to use in photography.For example, can enumerate the situation etc. of wishing to confirm the insertion position of the conduit of heart secondary lobe in performing the operation with this two dimensional surface radiation detecting apparatus.Under such situation, only an initial frame is photographed in whole camera coverage, in for the second time later frame, can carry out synthesizing after the photography of required part.Particularly, the ready or part of the part in the zone of photographing in moving image photographic by making the photography regional change at each frame, can increase the effect of accelerating picture rate when reading.For example, when carrying out moving image photographic with 30 frame/seconds, only photograph in whole camera coverage for 1 time in best 1 second, other 29 times/second are synthesized part photography zone with whole camera coverage.
In addition, knowing under the situation that move in this part photography zone, also can control this zone it is moved.For example, when the goods that is placed on the travelling belt is photographed, has the effect of power saving when move in the photography zone of two dimensional surface radiation detecting apparatus.
Figure 10 illustrates the synoptic diagram of power saving effect of the present invention.The area of the part that schematically illustrates with the straight line of time-power among Figure 10 is equivalent to total power consumption.According to the present invention, the area of the part of surrounding with oblique line has the effect of power saving.The effect of this power saving is divided into two kinds.A kind of is the power supply of the suitable components of photo-electric conversion of part by only importing and be designated as photography driving scope, makes the electric power that is positioned at the longitudinal axis reduce.
On the other hand by select only to drive the suitable row of part of scope with address decoder 94 with appointed photography, make electric charge (main reading) time after the x-ray bombardment of reading and the time of reading the electric charge (afterwards reading) of proofreading and correct usefulness shorten, therefore make time of power supply of the input amplifier components of photo-electric conversion shorten.According to these two effects, from electric power and times two aspect, make power consumption reduce the area of Figure 10 with oblique line encirclement part, this point is a feature of the present invention.
In addition, the part in the photography zone that the present invention carries out is specified, and can be used in combination in these operations also that the numeral that the high speed of reading with data is turned to the utilization sampling of purpose becomes doubly or pixel on average waits the reading method that combines.
Figure 11 illustrates the flow process in the embodiment of the invention.The position of X-ray generator and X ray camera at first is set.Then, select whether specify the X ray camera coverage, under not specified situation, drive the gamut of X ray camera.Under the situation of appointment, select the aperture of (i) X-ray tube, the device that (ii) is attached to the X ray camera, exposure field identifying information during a (iii) preceding shot, the (iv) relative position information between those who are investigated and the camera, (v) operate in the device of X ray camera more than one, the decision camera coverage.As the camera that is attached to (ii), for example, as shown in figure 11, the lip-deep button of the cabinet that is positioned at the X ray camera is shown.(ii), for situation at operator interface 22 enterprising line operates, owing in (ii), have at X-ray detector 52, specify the device of camera coverage on the slim X-ray detector 152, therefore preferably comparing with other has right of priority, also can not specify by the flow process of Figure 11 even make.That is, in the four corner that adopts the X ray camera or use (i)～(when v) having carried out the partly appointment of photography,, illustrate on the slim X-ray detector 152 and take which part at X-ray detector 52.If because photography failure or have no alternative but photograph once more, then the amount of being exposed is too much, therefore before photography preferably necessarily with reference to the demonstration of this camera coverage.When changing camera coverage, hope preferably use this right of priority (ii) to change.In addition, this right of priority (v), can provide right of priority to following situation, for example according to the situation of using the image that obtains from CCD camera etc. to carry out appointment, the situation of perhaps carrying out appointment on monitor.
Other embodiment
Offer a device or system by storing the storage medium that is used to implement according to the program code of the software of the function of the device of first or second embodiment or system with one, thereby the computing machine of this device or system (CPU, MPU etc.) reads and carries out the program code that is stored in this storage medium, also can realize purpose of the present invention.
In this case, realized the function of first or second embodiment, thereby stored storage medium and the present invention of program code formation itself of this program code from the program code self that this storage medium reads.
The storage medium of storing this program code for example can be ROM, floppy disk (floppy disk, registered trademark), hard disk, CD, magneto-optic disk, CD-ROM, CD-R, tape, Nonvolatile memory card etc.
In addition, not only read and carry out the function that this program code can be realized first or second embodiment by computing machine, and the OS that moves on computers according to the instruction utilization of this program code etc. can realize the function of first or second embodiment equally by the computing machine operating part or all handle.The latter also is one embodiment of the present of invention.
In addition, the program code that reads from storage medium can be write in the storer of the functional expansion unit that inserts the expansion board the computing machine or be connected to computing machine.By the CPU of this expansion board or functional expansion unit etc. according to the instruction operating part of this program code or all processing also can realize the function of first or second embodiment.This also is one of the present invention
Embodiment.
The present invention can be applied to program or store the storage medium of this program.
The present invention also can be applied to system that comprises a plurality of equipment (for example, radioactive ray generation equipment, X ray generation equipment, image processing equipment and interfacing equipment etc.) and the single equipment that can realize the function of these equipment.When the present invention was applied to the system that comprises a plurality of equipment, these equipment were each other for example by electricity, light and/or mechanical hook-up, and/or other device communications.
In addition, the present invention also can be applied to the diagnostic imaging backup system that comprises network (LAN and/or WAN etc.).
Thereby the present invention has realized above-mentioned purpose.
The invention is not restricted to the foregoing description, can carry out various changes and change within the spirit and scope of the present invention.Therefore, enclose following claims, so that scope of the present invention is informed the public.
Claims (5)
1. components of photo-electric conversion comprise:
Light is transformed to the optical detection device of electric signal;
Amplification is by the multiplying arrangement of the electric signal of this optical detection device output; And
The driving of this multiplying arrangement is carried out the drive unit of ON/OFF control.
2. X ray camera comprises:
By being used for that radioactive ray are transformed to the camera head that a plurality of components of photo-electric conversion of electric signal constitute;
A plurality of multiplying arrangements that electric signal from above-mentioned a plurality of components of photo-electric conversion output is amplified;
The driving of above-mentioned multiplying arrangement is carried out the drive unit of ON/OFF control.
3. X ray camera according to claim 2 is characterized in that, also comprises:
The read range specified device of the scope of the components of photo-electric conversion that appointment will be driven by this drive unit; And
Read signal reader by the output of the components of photo-electric conversion in the specified scope of this read range specified device.
4. X ray camera according to claim 3 is characterized in that:
Above-mentioned read range specified device shows the image that is photographed by above-mentioned camera head, and specifies the scope that reads the above-mentioned components of photo-electric conversion from shown image.
5. X ray camera comprises:
By being used for that light is transformed to the camera head that a plurality of components of photo-electric conversion of electric signal constitute;
Be used to specify the driving scope specified device of the scope that each components of photo-electric conversion that constitute above-mentioned camera head are driven;
The drive unit that the components of photo-electric conversion by the scope of above-mentioned driving scope specified device appointment are driven; And
Read the signal reader of the output of the components of photo-electric conversion that driven by above-mentioned drive unit;
Wherein, above-mentioned driving scope specified device is specified the scope that drives the above-mentioned components of photo-electric conversion by accompanying the coordinate entering device of above-mentioned camera head.
Applications Claiming Priority (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| JP154205/2002 | 2002-05-28 | ||
| JP2002154205 | 2002-05-28 |
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| CN1317568C true CN1317568C (en) | 2007-05-23 |
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| CNB031382894A Expired - Fee Related CN1317568C (en) | 2002-05-28 | 2003-05-26 | Optical detecting device x-ray photographic method and apparatus and photo-electric conversion components |
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| Publication number | Priority date | Publication date | Assignee | Title |
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| JP4110193B1 (en) * | 2007-05-02 | 2008-07-02 | キヤノン株式会社 | Solid-state imaging device and imaging system |
| BR112013014680A8 (en) * | 2010-12-15 | 2018-01-02 | Koninklijke Philips Electronics Nv | POWER SUPPLY UNIT FOR X-RAY RADIATION SOURCE, METHOD TO GENERATE DIFFERENT OUTPUT VOLTAGE LEVELS AND X-RAY IMAGE ACQUISITION SYSTEM |
| WO2015015718A1 (en) * | 2013-07-31 | 2015-02-05 | パナソニック インテレクチュアル プロパティ コーポレーション オブ アメリカ | Sensor assembly |
| JP6170863B2 (en) * | 2014-03-28 | 2017-07-26 | 富士フイルム株式会社 | Electronic cassette |
Citations (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US6229873B1 (en) * | 1999-09-30 | 2001-05-08 | Siemens Corporate Research, Inc | Method for aligning an apparatus for superimposing X-ray and video images |
| CN1295347A (en) * | 1999-10-07 | 2001-05-16 | 株式会社东芝 | Solid camera head |
| JP2001249183A (en) * | 2000-03-06 | 2001-09-14 | Matsushita Electric Ind Co Ltd | X-ray equipment |
| CN1340958A (en) * | 2000-07-28 | 2002-03-20 | 三菱电机株式会社 | Image transducer |
| JP2002141377A (en) * | 2000-11-01 | 2002-05-17 | Canon Inc | Tab tape and radiographic device |
-
2003
- 2003-05-26 CN CNB031382894A patent/CN1317568C/en not_active Expired - Fee Related
Patent Citations (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US6229873B1 (en) * | 1999-09-30 | 2001-05-08 | Siemens Corporate Research, Inc | Method for aligning an apparatus for superimposing X-ray and video images |
| CN1295347A (en) * | 1999-10-07 | 2001-05-16 | 株式会社东芝 | Solid camera head |
| JP2001249183A (en) * | 2000-03-06 | 2001-09-14 | Matsushita Electric Ind Co Ltd | X-ray equipment |
| CN1340958A (en) * | 2000-07-28 | 2002-03-20 | 三菱电机株式会社 | Image transducer |
| JP2002141377A (en) * | 2000-11-01 | 2002-05-17 | Canon Inc | Tab tape and radiographic device |
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