EP1250705B1 - Systeme de detection d'image radiologique pour generateur de rayons x a balayage - Google Patents
Systeme de detection d'image radiologique pour generateur de rayons x a balayage Download PDFInfo
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- EP1250705B1 EP1250705B1 EP00993753A EP00993753A EP1250705B1 EP 1250705 B1 EP1250705 B1 EP 1250705B1 EP 00993753 A EP00993753 A EP 00993753A EP 00993753 A EP00993753 A EP 00993753A EP 1250705 B1 EP1250705 B1 EP 1250705B1
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- Prior art keywords
- image
- image sensor
- detection system
- scanning
- irradiated
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- G—PHYSICS
- G21—NUCLEAR PHYSICS; NUCLEAR ENGINEERING
- G21K—TECHNIQUES FOR HANDLING PARTICLES OR IONISING RADIATION NOT OTHERWISE PROVIDED FOR; IRRADIATION DEVICES; GAMMA RAY OR X-RAY MICROSCOPES
- G21K1/00—Arrangements for handling particles or ionising radiation, e.g. focusing or moderating
- G21K1/02—Arrangements for handling particles or ionising radiation, e.g. focusing or moderating using diaphragms, collimators
- G21K1/04—Arrangements for handling particles or ionising radiation, e.g. focusing or moderating using diaphragms, collimators using variable diaphragms, shutters, choppers
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- G—PHYSICS
- G21—NUCLEAR PHYSICS; NUCLEAR ENGINEERING
- G21K—TECHNIQUES FOR HANDLING PARTICLES OR IONISING RADIATION NOT OTHERWISE PROVIDED FOR; IRRADIATION DEVICES; GAMMA RAY OR X-RAY MICROSCOPES
- G21K1/00—Arrangements for handling particles or ionising radiation, e.g. focusing or moderating
- G21K1/02—Arrangements for handling particles or ionising radiation, e.g. focusing or moderating using diaphragms, collimators
- G21K1/04—Arrangements for handling particles or ionising radiation, e.g. focusing or moderating using diaphragms, collimators using variable diaphragms, shutters, choppers
- G21K1/043—Arrangements for handling particles or ionising radiation, e.g. focusing or moderating using diaphragms, collimators using variable diaphragms, shutters, choppers changing time structure of beams by mechanical means, e.g. choppers, spinning filter wheels
Definitions
- the present invention relates to a detection system image for a scanning X-ray generator capable of operate at high speed.
- X-ray imaging systems comprising a system of X-ray image detection associated with an X-ray generator are used in the medical field or in the field of control not destructive. In these types of application, we seek to obtain images of very good quality and particularly well contrasted.
- a conventional X-ray imaging system used in the medical field generally includes an X-ray generator delivering X-rays to which a patient is exposed and, in contrast to the X-ray generator, a detection system that detects radiation X having passed through the patient and who is then carrying a radiological image.
- the X-ray generator and the patient are positioned relative to each other. each other so that the x-ray irradiation field covers at a instant given the entire surface to be imaged of the patient.
- the detection system stationary then simultaneously detects the radiological image of the entire surface to be imaged.
- This grid absorbs a large part of the scattered X-rays but also absorbs some useful x-rays, and therefore requires a dose higher patient.
- This grid is currently the only solution for eliminate diffuse in intensifier tube detection systems which are currently the most used to make real-time radiological imaging.
- Another solution to get rid of X-rays scattered without increasing the dose of x-rays involves using an x-ray generator scanning which irradiates the surface to be imaged in a progressive manner, the area instant irradiated being only a portion of the surface to be imaged.
- the X-ray generator is associated with a system mobile detection which is synchronized with the scanning movement of the X-ray and in geometric correspondence with the irradiated area Instant.
- the detection system is generally made up of elements solid state sensors covered with scintillator material and arranged in bar, the dimensions of this bar are such that it only receives the image of the instant irradiated area. It therefore does not detect the rays Scattered X which are deflected but which X-rays have passed directly through the patient.
- the dimensions of the bar are conditioned by those of the instant irradiated area. It is therefore not possible, without changing bar, to want to optimize the compromise between the dimensions of the area irradiated and the X-ray rate.
- the precision mechanics used to move the system detection represents an important item in the cost of such detection systems detection.
- the present invention while continuing to eliminate the scattering of radiological images, aims to overcome the above-mentioned problems, especially related to the doses to be administered to the patient, to the movement mechanics of the image sensor or other parts such as slots in shutters on the detection side; it allows to reach speeds compatible with those required in fluoroscopy mode.
- the present invention proposes a system of radiological image detection able to cooperate with a generator X-ray scanning to produce X-ray scanning a surface to be imaged, this X-ray irradiating portion after portion the surface to be imaged, X-ray radiation from a portion carrying an image radiological of said portion.
- the system includes an image sensor which is stationary with respect to the sweep and which is dimensioned to be able to acquire an image of the entire surface to be imaged via X-ray radiation portions, the detection system further comprising means electronic to limit, at a given time, the acquisition of the sensor image to an area corresponding to the portion irradiated at this time, these electronic limitation means being in synchronism with the scanning and in geometric correspondence with the irradiated portion.
- Electronic limitation means are purely static unlike rotating or scrolling mechanical limiting means of the prior art.
- the means to limit the acquisition of the image sensor can be means for partially obscuring the image sensor with respect to the surface to be imaged, external to the sensor image.
- a liquid crystal display whose scanning is controlled by synchronization with the scanning of the X-ray beam, makes it possible not to pass to a detection camera only a limited image area corresponding to that which is illuminated at this instant by the detector.
- the image sensor can be a bright image sensor and cooperate with means to convert X-rays from portions in bright image.
- the image sensor can be a electronic image sensor and cooperate with means to convert the X-ray from the portions directly in electronic image.
- the selenium sensors are able to do this direct conversion.
- the means to limit the acquisition of the sensor can be integrated into the image sensor, this being organized to prevent any image acquisition outside the area that corresponds to an image portion illuminated at an instant by the X-ray beam.
- the image sensor can be of the solid state type and in particular of the type CCD, CMOS type, with photosensitive diodes, with capacitive elements.
- the image sensor can be a light image sensor formed of a plurality of photosensitive pixels in the solid state, the means for limit the acquisition of the image sensor can order, just before that a portion is not irradiated, an erasure of the pixels of the sensor corresponding to the light image of said irradiated portion, and a reading of said pixels just after the irradiation of said portion.
- the image sensor can be a formed electronic image sensor of a plurality of capacitive elements and the means for limiting the acquisition of the image sensor can order just before a portion is irradiated, resetting the charge of the corresponding capacitive elements to the electronic image of said irradiated portion and a reading of the charges stored in said capacitive elements just after the irradiation of said portion.
- the light image sensor is of the film type. photographic or cinematographic film; in this case we will use principle a liquid crystal display to perform image limitation.
- Means for converting X-rays into bright images can be of radiological image intensifier or scintillator type deposited on a photosensitive matrix in the solid state, while the means to convert x-ray into electronic image can be realized based on selenium.
- the detection system may include means for processing the image captured by the image sensor so as to reconstruct an image complete radiological image of the surface to be imaged from the images irradiated areas.
- FIG. 1 represents an image detection system 20.
- This image detection system is used in imaging equipment medical comprising a scanning X-ray generator 10 which delivers a X-ray 1 scanning a surface to be imaged 2 of a patient 3 to be examined.
- the X-ray radiation only irradiates a portion 2 ′ of the surface to be imaged 2.
- the X-ray generator 10 at scan can be a slot scan, i.e. with a slot that moves in front of an X-ray source or be fixed slit as described by example in French patent application FR A- 2 795 864.
- the scanning speed may be high, in the absence of movements of mechanical parts.
- the detection system 20 On the other side of patient 3, i.e. opposite the generator 10 scanning x-ray is the detection system 20. It detects the X-ray 1 having passed through the patient, this X-ray being carrier of a radiological image.
- the image detection system 20 includes an image sensor 22 intended to acquire, via the X-ray radiation coming from the portions, an image of the surface to be imaged.
- This image sensor 22 is stationary with respect to the scan and it has dimensions allowing it to acquire an image of the entire surface to be imaged 2. It is neither set in motion nor limited in dimensions to those of the irradiated portion. By removing the means for set the sensor in motion since it is stationary, we get rid of in particular mechanical problems encountered with a sensor displaceable to the rhythm of the sweeping radiation.
- the image detection system 20 also includes means 24 to limit, at a given instant, the acquisition of the image sensor 22 essentially to that of the image of the portion 2 'irradiated at this instant, these means being in synchronism with the scan and in correspondence geometric with the irradiated portion 2 '.
- a dotted line illustrates the synchronism between the scanning X-ray 1 and the means 24 limiting the acquisition of the image sensor 22.
- the image sensor 22 is a sensor of bright image and it cooperates with means 21 to convert the X-ray carrying the radiological image into a bright image received by the light image sensor 22.
- the detection system 20 includes as image conversion means an image intensifier tube radiological 21 known by the acronym IIR, followed by the image sensor 22 light.
- the means 24 limiting the acquisition of the image sensor 22 light are mechanical means for partially obscuring the sensor 22 bright image. These partial concealment means 24 are external to the light image sensor 22, they partially mask the sensor image 22 so that it captures, at a given instant, only the image light of the portion irradiated 2 ′ by the scanning X 1 radiation.
- the IIR tube 21 conventionally comprises an enclosure 200 vacuum tight closed at one end by an entrance window 201 by which penetrates the scanning X-ray 1 having passed through the patient 3.
- the X-ray scanning 1 then meets an input screen 202 whose function is to translate the intensity of X-rays into a amount of electrons.
- This input screen 202 is dimensioned so as to be able to be struck by X 1 radiation regardless of the place of impact on the input window 201.
- the input screen 202 generally comprises a scintillator 203 associated with a photocathode 204.
- the scintillator 203 converts the scanning X-ray 1 into visible photons which are themselves converted to electrons by photocathode 204.
- a set of electrodes 205 accelerates the electrons and focuses them on a cathodoluminescent output screen 206.
- the output screen 206 luminescent is disposed near an exit window 207 located at opposite of the input window 201.
- the impact of electrons on the screen luminescent 206 allows to reconstruct the luminous image which has formed on photocathode 204. This bright image translates at a given time the radiological image of the irradiated portion 2 '.
- This bright image contains the faults mentioned above because with only the scanning X-ray, scattered X-rays strike photocathode 204 and their effect is visible on the output screen 206.
- This bright image sensor 22 is generally a CCD type sensor (for Charge-Coupled Device in English language or charge coupled device) included in a camera video 220, a cinematographic film placed in a camera cinematographic or photographic film included in a camera photographic.
- the CCD sensor can advantageously be replaced by a CMOS type sensor that works very similarly.
- the transmission of the bright image displayed by the screen of output 206 to the light image sensor 22 is generally done by via an optical coupling device 209, arranged outside of the IIR tube 21 and centered on a longitudinal axis XX 'of the IIR tube, axis around which is also centered the output screen 206.
- This optical device for coupling 209 may include lenses and / or optical fibers.
- the light image sensor 22 is sized to receive the entire image of the surface to be imaged 2, as is the case in conventional X-ray beam image detection systems stationary.
- the image detection system 20 may include a device signal acquisition and processing 23 which processes and stores signals relating to the image delivered to it by the light image sensor 22. After appropriate treatment, these signals can be observed on a display 25.
- the light image sensor 22 is stationary with respect to the scanning while the concealment means partial 24 are movable and more particularly rotatable relative to the 22 bright image sensor. They are placed between the output screen 206 and the light image sensor 22.
- This window 241 can simply be a opening in the disc which lets pass the bright image of the portion irradiated 2 '.
- the disc 240 is rotated so that its window 241 moves in synchronism with the X-ray 1 scanning the surface to be imaged 2.
- the window 241 has excursed the sensor bright image and the latter captured the entire radiological image of the surface to be imaged 2 converted into a light image, from a plurality of bright images corresponding to the different irradiated portions 2 ' during scanning.
- the rotation speed of the disc 240 is synchronized with that of the X-ray beam scanning 1.
- the scanning of X-ray 1 scanning takes place on the surface to be imaged 2 from top to bottom as shown in the figure 1.
- the X-ray scanning 1 emerges from a slit 4 whose length, perpendicular to the direction of the scan, corresponds to the dimension of the surface to be imaged 2 also located perpendicular to the scanning direction, to within an enlargement coefficient.
- This factor is a function of the distance between patient 3 and the X-ray generator 10.
- the width of the slot 4 located in the scanning direction is very small in front of the other dimension of the surface to be imaged 2 also located in the scanning direction.
- the slot 4 can be moved back and forth in translation, but we can consider, to overcome this back and forth movement which is always difficult to perform at large speed, to use a rotating disc with a or more slots. In this case the scanning is unidirectional.
- the dimensions of the irradiated portion 2 'at a given time are modeled on those of slot 4 to the nearest magnification.
- the windows 241 are slots radial whose dimensions are modeled on those of the irradiated portion 2 ', to within a proportionality coefficient, function of the relative positions and effects of the different elements between patient 3 and the concealment means 24.
- These slots 241 are located at the periphery of the disc 240. It is better to distribute windows 241 around the entire periphery of the disk especially if the rate of radiological images to be taken is high.
- the disc 240 will have a large radius in front of the length of windows 241 so that the displacement of a slit in front of the light image sensor 22 either comparable to a translation.
- the disc 240 will have a large radius in front of the length of windows 241 so that the displacement of a slit in front of the light image sensor 22 either comparable to a translation.
- the partial concealment means 24 can take the form of an opaque ribbon 242 provided with one or more windows 243 transparent to the exit screen light 206.
- This strip 242 can be configured in loop and driven by rollers 244 as illustrated in Figure 3. When is facing the light image sensor 22, it moves in translation. His windows 243 are slots transverse to the direction of travel of the ribbon 242. Reference is made to FIG. 4.
- the X-ray emission can be stopped during one of the two journeys if the partial concealment means have a unidirectional movement in rotation or translation.
- the concealment means 24 partial are arranged between the output screen 206 and the image sensor 22 light.
- the partial concealment means 24 can be located either between the screen of output 206 and the optical coupling device 209 as in FIG. 1, or between the optical coupling device 209 and the image sensor 22 as shown in Figure 3.
- the means of concealment 24 partial are placed between the patient 3 and the conversion means 21 and that they are directly exposed to X-ray.
- the image sensor could be an electronic image sensor.
- the image sensor is a light image sensor and the conversion means 21 are materialized by an IIR tube.
- the partial concealment means 24 are exposed directly to X-ray 1 having passed through patient 3 and have an opaque part 247 with X-rays and one or more parts 248 which lets him pass.
- the partial concealment means 24 take the form of a disc which forms the opaque part 247 and that this disc has windows 248 in the form of slits which allow the radiological image of the irradiated portion 2 ′ to pass.
- These partial concealment means 24 having to be partially opaque to the X-rays are made from lead and require resources more powerful to be moved and more expensive than in the variants preceding.
- the present invention proposes to use means electronic, synchronized with the X-ray scanning movement, to produce an electronic image only in an area that given moment, corresponding to the area irradiated by the X-ray in sweeping movement.
- These means are static and replace advantageously the mechanical means described above, in the different configurations envisaged.
- a liquid crystal screen is inserted between the luminous image and an image sensor.
- This image sensor is preferably electronic (such as the CCD or CMOS matrix sensor of an electronic camera) but we can also consider that it is a simple photographic film which will be exposed area by area as the X-ray is scanned, the film areas that do not correspond to the area irradiated at one time given being hidden at this time.
- the liquid crystal display is rendered opaque everywhere except in an area (in principle a matrix line if the scanning allows line-by-line irradiation) corresponding to the image actually irradiated by the X-ray.
- the light image sensor if is electronic, does not collect a signal, except in this area.
- the X-rays which may have been scattered in scattered directions and which may have produce a bright image not limited to the irradiated portion, will not influence the electronic sensor because it will only observe one area corresponding to the irradiated portion.
- the means of integration electronics that convert bright image photons or photons of image X into electrons are organized to prevent integration or reading of charges outside the image area which corresponds to the area irradiated at a given time by the scanning X-ray.
- the partial concealment means 24 are produced by a network shutter 245 with liquid crystal transmission subject to the position of the portion irradiated 2 'by X-ray radiation 1 sweeping. These partial concealment means 24 are used to stop the light from the output screen 206 of the image intensifier tube radiological 21.
- This shutter 245 may comprise a thin layer 31 of liquid crystals (for example of nematic type in helix) taken in sandwich between two transparent blades 32, 33 sealed together, they same placed between two crossed polarizers 36.
- liquid crystals for example of nematic type in helix
- Such a shutter 245 operates in the following manner. At least one of the transparent blades is provided with an array of electrodes. for applying an electric field to portions of the liquid crystals. This is why the shutter 245 is said to be networked. In subjecting part of the liquid crystal layer to a field electric, it becomes opaque and stops the light coming from the screen of output 206. This light can no longer reach image sensor 22 light. In the absence of an electric field, this part is transparent and lets in the light coming from the output screen 206. This light can thus reach the light image sensor 22.
- each plate 32 33 transparent a network 34, 35 of parallel transparent electrodes E1, E2 oriented transversely to the direction of X-ray scanning 1.
- An electrode E1 of a network 34 is paired with an electrode E2 of the other network 35 and two electrodes matched are opposite.
- Each network 34, 35 is connected to a device for command respectively 37, 38 making it possible to apply to its electrodes E1, E2 an appropriate potential and therefore subject to an electric field suitable for the portion of liquid crystal between two electrodes matched to make it opaque.
- the order of potentials to apply to the electrodes carried out in synchronism with the scanning allows, at each instant, to include in the obturator 245 opaque a transparent zone 246 whose dimensions are such that the light image sensor 22 does not captures only the radiological image of the irradiated portion 2 '.
- the dimensions of the transparent zone 246 are modeled on those of the irradiated portion 2 'at proportionality coefficient.
- Electrodes patterns depicted in Figure 7 are only non-limiting examples and others are of course possible to delimit what should remain opaque and what should become transparent.
- a pattern conventional matrix can be used, provided that the control means, in principle line by line, are organized so as to correspond with the nature of the X scan used.
- a significant advantage of the means to limit the acquisition the image sensor associated with an X-ray image intensifier tube, in the configuration where they are located between the output screen and the sensor picture is that these limiting means don't just eliminate the light from the X-ray scattered in the patient but also scattered light and X-rays scattered along the entire path between them and the patient. In their absence, this light or this X-ray would be captured by the image sensor and the contrast would be degraded. The best gains in contrast are obtained by placing the most limiting means possible near the light image sensor.
- the scanning X-ray generator 10 which delivers the X-ray radiation 1 scanning the surface to be imaged 2 of a patient 3 to be examined.
- the detection system 20 On the other side of the patient 3 is the detection system 20 according to the invention with a light image sensor 22. It includes means 21 for converting the X-ray from the 2 'portions in an IIR tube type light image associated with the light image sensor 22.
- the image sensor 22 luminous is a CMOS type electronic sensor included for example in a video camera 220.
- the means 240 for limiting the acquisition of the light image sensor are integrated into the light image sensor.
- CMOS type sensors are starting to be used. They are very promising because they consume much less that CCD sensors, are much less bulky, offer new possibilities in the acquisition of portions of images, can operate at higher speeds than CCD sensors and are costly lower.
- each pixel does not only have one photosensor element, for example a photodiode, but also a circuit CMOS transistor with reading amplifier function allowing power quickly read the quantity of charges stored at the level of each pixel which was exposed to a light signal.
- On the same substrate there are also means for digitizing the signals stored by the pixels and used during reading.
- the sensor 22 bright image is formed by a plurality of sensitive points or pixels P1 to P9 photosensitive arranged in a matrix and connected between a column conductor Y1 to Y3 and a row conductor X1 to X3. These pixels are symbolized by a square. We only represented nine for do not overload the figure.
- the pixels P1 to P3 connected to the same line conductor X1 are addressed in at the same time by an addressing device 400 connected to the conductors of line X1 to X3, the amount of light they received is read at each pixel, the data read for each pixel being transferred by the column conductors Y1 to Y3 in a conversion device analog-digital 401 operating in parallel to be digitized there.
- the means 240 limiting the acquisition of the image sensor 22, in a first phase, just before a 2 'portion is irradiated, control the reset to zero, i.e. the erasure of pixels P4 to P6 of the sensor corresponding to the light image of said portion, and in a second phase, just after the 2 'portion has been irradiated, order the reading of the pixels P4 to P6 corresponding to this bright image. For acquire the bright image of the surface to be imaged 2 all the pixels are subject to this succession of states erasure, exposure, reading.
- Figures 9a to 9c are used to describe the operation of the means 240. It is assumed that the scanning of X-ray 1 is done linearly as in Figure 1 and that a line of pixels corresponds to a 2 'irradiated portion. The arrow entering block 240 symbolizing the limitation means indicates that these means are synchronized with the X-ray scanning movement.
- the line conductor X2 to which the pixels P4 to P6 carries an arrow from the addressing device 400, which symbolizes that they have just been deleted or set to zero. They were emptied of any traces of previous exposure. Pixels P1 to P3 are exposed and are shown grayed out while pixels P7 to P9 are read, which is symbolized by arrows on the column conductors Y1 to Y3 from pixels P7 to P9 and directed to the analog-digital conversion device 401.
- the pixels P4 to P6 are grayed out, which means that they have just been exposed to an illumination delivered by the intensifier tube radiological image.
- Pixels P1 to P3 are read, which is symbolized by arrows on the column conductors Y1 to Y3 from pixels P1 to P3 and directed to the analog-digital conversion device 401.
- the pixels P7 to P9 are erased which is symbolized by the arrow, from the addressing device 400, and carried by the line conductor X3 to which pixels P7 to P9 are connected.
- FIG. 9c we wanted to illustrate the fact that the pixels P4 to P6 are read at this time while the pixels P1 to P3 are erased and the pixels P7 to P9 are exposed.
- the same symbols as before have been used. In this way, the signals read do not include a broadcast.
- the generator 10 x-ray scanning which delivers x-ray 1 scanning the surface at image 2 of a patient 3 to be examined.
- the detection system 20 On the other side of patient 3 is the detection system 20 according to the invention.
- IIR tube There is no IIR tube. It comprises a solid state image sensor 22, 52 which can be either of the sensor type light image 22, or of the electronic image sensor type 52. Its dimensions are substantially those of the surface to be imaged 2.
- the sensor cooperates with means 21, 51 for converting X-ray radiation from 2 'portions either as a light image or as an electronic image. If it is about of a conversion into a bright image, the conversion means 21 are of scintillator type which cover the light image sensor 22.
- the conversion means 51 are made from selenium which covers the electronic image sensor 52.
- the conversion means 21, 51 are directly facing the X-ray who crossed the patient.
- the light image sensor 22 can be a sensor whose pixels are formed by a cooperating photosensitive diode with a switch. This type of sensor is well known in radiology digital.
- the electronic image sensor 52 can comply with what shows FIG. 10.
- the means 240 for limiting the acquisition of the sensor are integrated in the image sensor 22, 52 and quite comparable to what has been described in figure 8a
- the sensitive elements of the sensor are subject to a succession of states: erasure or reset, exposure, reading.
- the electronic image sensor 52 is formed of a plurality of points 53 sensitive to electronic charges, each formed of a capacitive element 54 associated with an element of switching 55 for example a TFT transistor (for the Anglo-Saxon designation Thin Film Transistor) activated especially during playback, arranged in a network like the representations in Figures 9. These points sensitive are made in particular using film deposition technique thin semiconductor materials such as amorphous silicon.
- This electronic image sensor 52 cooperates with conversion means 51 radiological image - electronic image based on selenium for example.
- the sensitive points are covered with a layer 51 based on selenium. When crossing the selenium-based layer 51 the X-ray is directly converted into electronic charges (symbolized by an arrow).
- These electronic charges are stored on the capacitive elements 54.
- the means for limiting the acquisition of the electronic image sensor operate in a manner comparable to what has been described in FIGS. 8a and 8b.
- the charges stored on the capacitive elements 54 are read sequentially line by line. By performing a surrender operation zero of the capacitive elements 54 of a line just before they receive electronic charges and a read operation of stored charges in these capacitive elements right after they have received charges, we manages to eliminate the signal linked to the x-rays scattered in the acquisition of the radiological image.
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Abstract
Description
- la figure 1 une coupe d'un exemple de système de détection d'image associé à un générateur de rayons X à balayage, dans lequel les moyens de limitation de l'acquisition du capteur d'image sont des moyens d'occultation partielle mécaniques ;
- la figure 2 une vue de face des moyens limitant l'acquisition du capteur d'image utilisés dans le système de détection d'image de la figure 1 ;
- la figure 3 une coupe d'un second exemple de système de détection d'image associé à un générateur de rayons X à balayage, dans lequel les moyens de limitation de l'acquisition du capteur d'image sont des moyens d'occultation partielle mécaniques ;
- la figure 4 une vue de face des moyens limitant l'acquisition du capteur d'image utilisés dans le système de détection d'image de la figure 3 ;
- la figure 5 une coupe d'un troisième exemple de système de détection d'image associé à un générateur de rayons X à balayage, dans lequel les moyens de limitation de l'acquisition du capteur d'image sont des moyens d'occultation partielle mécaniques ;
- la figure 6 une coupe d'un quatrième exemple de système de détection d'image selon l'invention associé à un générateur de rayons X à balayage, dans lequel les moyens de limitation de l'acquisition du capteur d'image sont des moyens d'occultation partielle électroniques et externes au capteur d'image ;
- la figure 7 une vue de face des moyens d'occultation partielle utilisés dans le système de détection d'image de la figure 6 ;
- les figures 8a, 8b, en coupe, deux nouveaux exemples de système de détection d'image selon l'invention dans lesquels les moyens limitant l'acquisition du capteur d'image sont intégrés au capteur d'image ;
- les figures 9a, 9b, 9c trois vues de face du capteur d'image de la figure 8a, à des instants différents, permettant de comprendre le fonctionnement des moyens limitant son acquisition ;
- la figure 10, en coupe partielle un capteur d'image électronique pouvant être intégré dans un système de détection d'image selon l'invention.
Claims (12)
- Système de détection d'image radiologique apte à coopérer avec un générateur de rayons X (10) à balayage destiné à produire un rayonnement X (1) balayant une surface à imager (2), ce rayonnement X (1) irradiant portion (2') après portion la surface à imager (2), le rayonnement X issu d'une portion (2') étant porteur d'une image radiologique de ladite portion, le système comportant un capteur d'image (22, 52) qui est stationnaire vis à vis du balayage et qui est dimensionné pour pouvoir acquérir une image de toute la surface à imager (2) via le rayonnement X issu des portions (2'), caractérisé en ce que le système de détection comporte de plus des moyens électroniques pour limiter, à un instant donné, l'acquisition du capteur d'image (22,52) à une zone correspondant à la portion irradiée (2') à cet instant, ces moyens de limitation agissant en synchronisme avec le balayage et en correspondance géométrique avec la portion irradiée (2').
- Système de détection d'image selon la revendication 1, caractérisé en ce que le capteur d'image est un capteur (22) d'image lumineuse et en ce qu'il coopère avec des moyens pour convertir le rayonnement X issu des portions (2') en image lumineuse.
- Système de détection d'image selon la revendication 2, caractérisé en ce que les moyens (24) pour limiter l'acquisition sont réalisés par un obturateur (245) à cristaux liquides en réseau, fixe par rapport au capteur d'image (22) lumineuse et intercalé entre les moyens pour convertir le rayonnement X en image lumineuse et le capteur d'image lumineuse.
- Système de détection d'image selon l'une des revendications 1 et 2 caractérisé en ce que les moyens (240) pour limiter l'acquisition du capteur d'image (22) sont intégrés au capteur d'image.
- Système de détection d'image selon la revendication 4, dans lequel le capteur d'image (22) est formé d'une pluralité de pixels photosensibles à l'état solide, caractérisé en ce que les moyens (240) pour limiter l'acquisition du capteur d'image (22) commandent juste avant qu'une portion ne soit irradiée, un effacement des pixels du capteur correspondants à l'image lumineuse de ladite portion irradiée, et une lecture desdits pixels juste après l'irradiation de la dite portion.
- Système de détection d'image selon la revendication 4, dans lequel le capteur d'image électronique est formé d'une pluralité d'éléments capacitifs (54), caractérisé en ce que les moyens (240) pour limiter l'acquisition du capteur d'image (52) commandent, juste avant qu'une portion (2') ne soit irradiée une mise à zéro des éléments capacitifs (54) correspondant à l'image électronique de ladite portion irradiée et une lecture des charges stockées dans lesdits éléments capacitifs (54) juste après l'irradiation de la dite portion (2').
- Système de détection selon l'une des revendications 1 à 4, caractérisé en ce que le capteur d'image (22, 52) est de type état solide et notamment de type CCD, de type CMOS, à diodes photosensibles, à éléments capacitifs.
- Système de détection selon la revendication 2, caractérisé en ce que les moyens (21) pour convertir le rayonnement X en image lumineuse sont de type intensificateur d'image radiologique ou scintillateur.
- Système de détection d'image selon la revendication 1, caractérisé en ce que le capteur d'image (52) est un capteur d'image électronique et en ce qu'il coopère avec des moyens (51) pour convertir directement le rayonnement X issu des portions (2') en image électronique.
- Système de détection selon la revendication 9, caractérisé en ce que les moyens (51) pour convertir le rayonnement X en image électronique sont réalisés à base de sélénium.
- Système de détection selon l'une des revendications 1 à 10, caractérisé en ce qu'il comporte des moyens (23) de traitement de l'image captée par le capteur d'image (22) de manière à reconstruire une image complète de l'image radiologique de la surface à imager à partir des images des zones irradiées.
- Système de détection selon l'une des revendications 1 à 3, caractérisé en ce que le capteur d'image lumineuse est de type film photographique ou film cinématographique.
Applications Claiming Priority (3)
Application Number | Priority Date | Filing Date | Title |
---|---|---|---|
FR9916778A FR2803394B1 (fr) | 1999-12-30 | 1999-12-30 | Systeme de detection d'image radiologique pour generateur de rayons x a balayage |
FR9916778 | 1999-12-30 | ||
PCT/FR2000/003723 WO2001050481A1 (fr) | 1999-12-30 | 2000-12-28 | Systeme de detection d'image radiologique pour generateur de rayons x a balayage |
Publications (2)
Publication Number | Publication Date |
---|---|
EP1250705A1 EP1250705A1 (fr) | 2002-10-23 |
EP1250705B1 true EP1250705B1 (fr) | 2004-05-06 |
Family
ID=9554086
Family Applications (1)
Application Number | Title | Priority Date | Filing Date |
---|---|---|---|
EP00993753A Expired - Lifetime EP1250705B1 (fr) | 1999-12-30 | 2000-12-28 | Systeme de detection d'image radiologique pour generateur de rayons x a balayage |
Country Status (5)
Country | Link |
---|---|
US (2) | US6934360B2 (fr) |
EP (1) | EP1250705B1 (fr) |
DE (1) | DE60010521T2 (fr) |
FR (1) | FR2803394B1 (fr) |
WO (1) | WO2001050481A1 (fr) |
Families Citing this family (8)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
FR2879183B1 (fr) * | 2004-12-15 | 2007-04-27 | Atmel Grenoble Soc Par Actions | Procede de fabrication collective de microstructures a elements superposes |
FR2906400B1 (fr) | 2006-09-26 | 2008-11-14 | Thales Sa | Correction de distorsion d'un tube electronique intensificateur d'image. |
EP1916696B1 (fr) * | 2006-10-25 | 2017-04-19 | ICT, Integrated Circuit Testing Gesellschaft für Halbleiterprüftechnik mbH | Détecteur pour particules chargées, appareil des particules chargées et méthode de formation d'une image |
EP2380015A4 (fr) | 2008-12-30 | 2016-10-26 | Sikorsky Aircraft Corp | Procédé d'inspection non destructive avec une évaluation objective |
US8440978B2 (en) * | 2010-10-22 | 2013-05-14 | Varian Medical Systems International Ag | Method and apparatus for multi-layered high efficiency mega-voltage imager |
FR2975213B1 (fr) | 2011-05-10 | 2013-05-10 | Trixell Sas | Dispositif d'adressage de lignes d'un circuit de commande pour matrice active de detection |
FR2978566B1 (fr) * | 2011-07-25 | 2016-10-28 | Commissariat Energie Atomique | Systeme d'imagerie pour l'imagerie d'objets a mouvement rapide |
US9666419B2 (en) * | 2012-08-28 | 2017-05-30 | Kla-Tencor Corporation | Image intensifier tube design for aberration correction and ion damage reduction |
Family Cites Families (13)
Publication number | Priority date | Publication date | Assignee | Title |
---|---|---|---|---|
EP0073543A3 (fr) | 1981-08-28 | 1984-02-22 | Jacques Piquerez | Système de transmission d'informations entre un appareil de téléphone et une personne éloignée de son appareil |
US4404591A (en) * | 1982-01-04 | 1983-09-13 | North American Philips Corporation | Slit radiography |
US4649559A (en) * | 1983-10-31 | 1987-03-10 | Xonics Imaging, Inc. | Digital radiography device |
DE8714009U1 (de) * | 1987-10-19 | 1989-02-16 | Siemens AG, 1000 Berlin und 8000 München | Röntgendiagnostikvorrichtung |
JPH0318352A (ja) * | 1989-06-16 | 1991-01-25 | Toshiba Corp | X線診断装置 |
JP2670632B2 (ja) * | 1990-01-12 | 1997-10-29 | 富士写真フイルム株式会社 | 光走査装置 |
US5434418A (en) * | 1992-10-16 | 1995-07-18 | Schick; David | Intra-oral sensor for computer aided radiography |
US5682411A (en) * | 1993-06-16 | 1997-10-28 | St. John Innovation Centre | Imaging system |
DE69833128T2 (de) * | 1997-12-10 | 2006-08-24 | Koninklijke Philips Electronics N.V. | Bildung eines zusammengesetzten bildes aus aufeinanderfolgenden röntgenbildern |
JP3447947B2 (ja) * | 1998-03-20 | 2003-09-16 | 株式会社東芝 | X線撮像装置 |
FR2777112B1 (fr) | 1998-04-07 | 2000-06-16 | Thomson Tubes Electroniques | Dispositif de conversion d'une image |
CA2241779C (fr) * | 1998-06-26 | 2010-02-09 | Ftni Inc. | Detecteur d'image radiologique indirecte pour utilisation avec la radiologie |
AU2001246853A1 (en) * | 2000-04-06 | 2001-10-23 | Hamamatsu Photonics K.K. | X-ray inspection system |
-
1999
- 1999-12-30 FR FR9916778A patent/FR2803394B1/fr not_active Expired - Fee Related
-
2000
- 2000-12-28 DE DE60010521T patent/DE60010521T2/de not_active Expired - Lifetime
- 2000-12-28 WO PCT/FR2000/003723 patent/WO2001050481A1/fr active IP Right Grant
- 2000-12-28 EP EP00993753A patent/EP1250705B1/fr not_active Expired - Lifetime
- 2000-12-28 US US10/129,818 patent/US6934360B2/en not_active Expired - Lifetime
-
2005
- 2005-05-09 US US11/124,268 patent/US7082187B2/en not_active Expired - Lifetime
Also Published As
Publication number | Publication date |
---|---|
DE60010521D1 (de) | 2004-06-09 |
US20020172327A1 (en) | 2002-11-21 |
US20050201518A1 (en) | 2005-09-15 |
US6934360B2 (en) | 2005-08-23 |
DE60010521T2 (de) | 2005-05-12 |
WO2001050481A1 (fr) | 2001-07-12 |
EP1250705A1 (fr) | 2002-10-23 |
FR2803394A1 (fr) | 2001-07-06 |
FR2803394B1 (fr) | 2003-04-25 |
US7082187B2 (en) | 2006-07-25 |
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