WO2016120091A1 - Capteur radiologique avec detection de rayons x - Google Patents
Capteur radiologique avec detection de rayons x Download PDFInfo
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- WO2016120091A1 WO2016120091A1 PCT/EP2016/050730 EP2016050730W WO2016120091A1 WO 2016120091 A1 WO2016120091 A1 WO 2016120091A1 EP 2016050730 W EP2016050730 W EP 2016050730W WO 2016120091 A1 WO2016120091 A1 WO 2016120091A1
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- pixels
- photodiodes
- detection
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- 238000001514 detection method Methods 0.000 title claims abstract description 56
- 230000005855 radiation Effects 0.000 title description 2
- 239000004020 conductor Substances 0.000 claims abstract description 47
- 239000011159 matrix material Substances 0.000 claims description 39
- 238000005516 engineering process Methods 0.000 claims description 7
- 238000005286 illumination Methods 0.000 claims description 4
- 238000002059 diagnostic imaging Methods 0.000 abstract description 2
- 230000010354 integration Effects 0.000 description 10
- 230000008520 organization Effects 0.000 description 8
- 238000012163 sequencing technique Methods 0.000 description 5
- 230000000694 effects Effects 0.000 description 4
- XUIMIQQOPSSXEZ-UHFFFAOYSA-N Silicon Chemical compound [Si] XUIMIQQOPSSXEZ-UHFFFAOYSA-N 0.000 description 3
- 238000006243 chemical reaction Methods 0.000 description 3
- 229910052710 silicon Inorganic materials 0.000 description 3
- 239000010703 silicon Substances 0.000 description 3
- NCAJWYASAWUEBY-UHFFFAOYSA-N 3-[20-(2-carboxyethyl)-9,14-diethyl-5,10,15,19-tetramethyl-21,22,23,24-tetraazapentacyclo[16.2.1.1^{3,6}.1^{8,11}.1^{13,16}]tetracosa-1(21),2,4,6(24),7,9,11,13,15,17,19-undecaen-4-yl]propanoic acid Chemical compound N1C2=C(C)C(CC)=C1C=C(N1)C(C)=C(CC)C1=CC(C(C)=C1CCC(O)=O)=NC1=CC(C(CCC(O)=O)=C1C)=NC1=C2 NCAJWYASAWUEBY-UHFFFAOYSA-N 0.000 description 2
- 238000010586 diagram Methods 0.000 description 2
- 238000003384 imaging method Methods 0.000 description 2
- 238000012432 intermediate storage Methods 0.000 description 2
- 238000004519 manufacturing process Methods 0.000 description 2
- 239000000463 material Substances 0.000 description 2
- 238000013475 authorization Methods 0.000 description 1
- 238000004891 communication Methods 0.000 description 1
- 210000004513 dentition Anatomy 0.000 description 1
- 238000003745 diagnosis Methods 0.000 description 1
- 229910021421 monocrystalline silicon Inorganic materials 0.000 description 1
- 238000000059 patterning Methods 0.000 description 1
- 230000000737 periodic effect Effects 0.000 description 1
- 238000001228 spectrum Methods 0.000 description 1
- 238000003860 storage Methods 0.000 description 1
- 230000036346 tooth eruption Effects 0.000 description 1
- 230000001960 triggered effect Effects 0.000 description 1
Classifications
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- A61B6/512—
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- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B5/00—Measuring for diagnostic purposes; Identification of persons
- A61B5/0059—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence
- A61B5/0082—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence adapted for particular medical purposes
- A61B5/0088—Measuring for diagnostic purposes; Identification of persons using light, e.g. diagnosis by transillumination, diascopy, fluorescence adapted for particular medical purposes for oral or dental tissue
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
- A61B6/42—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment with arrangements for detecting radiation specially adapted for radiation diagnosis
- A61B6/4208—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment with arrangements for detecting radiation specially adapted for radiation diagnosis characterised by using a particular type of detector
- A61B6/4233—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment with arrangements for detecting radiation specially adapted for radiation diagnosis characterised by using a particular type of detector using matrix detectors
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
- A61B6/52—Devices using data or image processing specially adapted for radiation diagnosis
- A61B6/5205—Devices using data or image processing specially adapted for radiation diagnosis involving processing of raw data to produce diagnostic data
-
- A—HUMAN NECESSITIES
- A61—MEDICAL OR VETERINARY SCIENCE; HYGIENE
- A61B—DIAGNOSIS; SURGERY; IDENTIFICATION
- A61B6/00—Apparatus for radiation diagnosis, e.g. combined with radiation therapy equipment
- A61B6/54—Control of apparatus or devices for radiation diagnosis
- A61B6/545—Control of apparatus or devices for radiation diagnosis involving automatic set-up of acquisition parameters
-
- G—PHYSICS
- G01—MEASURING; TESTING
- G01T—MEASUREMENT OF NUCLEAR OR X-RADIATION
- G01T1/00—Measuring X-radiation, gamma radiation, corpuscular radiation, or cosmic radiation
- G01T1/16—Measuring radiation intensity
- G01T1/20—Measuring radiation intensity with scintillation detectors
- G01T1/2018—Scintillation-photodiode combinations
- G01T1/20184—Detector read-out circuitry, e.g. for clearing of traps, compensating for traps or compensating for direct hits
-
- H—ELECTRICITY
- H04—ELECTRIC COMMUNICATION TECHNIQUE
- H04N—PICTORIAL COMMUNICATION, e.g. TELEVISION
- H04N25/00—Circuitry of solid-state image sensors [SSIS]; Control thereof
- H04N25/40—Extracting pixel data from image sensors by controlling scanning circuits, e.g. by modifying the number of pixels sampled or to be sampled
-
- H—ELECTRICITY
- H04—ELECTRIC COMMUNICATION TECHNIQUE
- H04N—PICTORIAL COMMUNICATION, e.g. TELEVISION
- H04N25/00—Circuitry of solid-state image sensors [SSIS]; Control thereof
- H04N25/70—SSIS architectures; Circuits associated therewith
-
- H—ELECTRICITY
- H04—ELECTRIC COMMUNICATION TECHNIQUE
- H04N—PICTORIAL COMMUNICATION, e.g. TELEVISION
- H04N3/00—Scanning details of television systems; Combination thereof with generation of supply voltages
- H04N3/10—Scanning details of television systems; Combination thereof with generation of supply voltages by means not exclusively optical-mechanical
- H04N3/14—Scanning details of television systems; Combination thereof with generation of supply voltages by means not exclusively optical-mechanical by means of electrically scanned solid-state devices
- H04N3/15—Scanning details of television systems; Combination thereof with generation of supply voltages by means not exclusively optical-mechanical by means of electrically scanned solid-state devices for picture signal generation
- H04N3/155—Control of the image-sensor operation, e.g. image processing within the image-sensor
-
- H—ELECTRICITY
- H04—ELECTRIC COMMUNICATION TECHNIQUE
- H04N—PICTORIAL COMMUNICATION, e.g. TELEVISION
- H04N5/00—Details of television systems
- H04N5/30—Transforming light or analogous information into electric information
- H04N5/32—Transforming X-rays
Definitions
- the invention relates to medical imaging and more particularly to intra-oral dental radiology.
- Recent dental radiology systems utilize silicon-based MOS technology image sensors coated with a layer of scintillator material that converts X-rays into visible light in a wavelength spectrum to which silicon is sensitive.
- the image sensor integrates electrical charges generated by the light which itself is generated by the scintillator.
- the sensor comprises a matrix of active pixels, each pixel comprising a photosensitive element (most often a photodiode) and some transistors for collecting the charges generated by the light in the pixel to convert them into voltage.
- a sequencing circuit ensures the operation of the whole of the sensor to ensure the reinitialization of the pixels, then the integration of charges from an integration start time and for a certain duration, and finally the reading of the voltages representing the electrical charges accumulated in the pixels. The reading of these voltages is done by a reading circuit placed at the foot of each of the columns of pixels of the matrix.
- the reading of a line of pixels is done by simultaneously addressing all the pixels of this line using a line decoder; for this, the pixels each comprise a line selection transistor which is made conductive under the control of the line decoder, and this simultaneously for all the pixels of the same line.
- the line selection transistor then connects the pixel to a respective column conductor, common to all the pixels of the same column of pixels, to transfer on this column conductor a useful signal representing the charges generated in the pixel at the intersection of the selected line and the column in question.
- the transfer is done simultaneously for all the pixels of the line, each to its respective column driver.
- the X-ray sensor is placed behind the human body part to be observed: for an intra-oral dental X-ray sensor, it is placed in the patient's mouth near the dental region to be observed.
- An X-ray source is placed outside the mouth of the patient, in front of the sensor and exposes it with a short X-ray flash, through the biological tissue or other material to be observed.
- One solution is to use a wired connection between the sensor and the X-ray source to trigger the integration of an electronic image at the same time as starting the X-ray source.
- the wired connection requires a common protocol between the sensor and the source, which is hardly compatible with the fact that the sensor should be able to be exposed by any source, or vice versa that the source should be able to illuminate any sensor.
- the resulting voltage level is continuously monitored; it represents a dark current noise before the start of an X-ray flash; if this level increases significantly, it means that a flash X has started and can trigger a complete image.
- This solution can not be transposed to CMOS sensors that do not have a read charge transfer register; in addition, it disrupts the operation of the sensor by making the central photosensitive register while it reads the charges generated in the matrix, which deteriorates the image.
- pixels distributed in the matrix are used as reference pixels and are monitored to trigger the image taking if the level of a certain number of these reference pixels exceeds a threshold. This requires specific addressing means to read the reference pixels. This is also the case if reference areas of several pixels are used to make this detection.
- a detection cell larger than one pixel and able to surround the entire matrix is provided to detect the arrival of a flash X. This solution is cumbersome and the detection may be done in a place where little X-rays arrive because of the obstacles they have to cross.
- the overall image read by the pixels is compared to an image taken in the dark before exposure to X-rays.
- the image read becomes sharply different from the image taken in the dark, it is concluded that the flash has started. This requires reading the entire matrix to have this information abrupt change of brightness level of the complete image.
- the pixel array is read with subsampling, i.e. all pixels are not read; only rows of pixels located at the periphery are actually read to detect the arrival of X-rays. This complicates the internal organization of the sensor and its sequencing circuits.
- the detection threshold is scalable and depends on the previous image, to take into account that the dark current of the pixels that detect the arrival of the flash X depends on the ambient temperature conditions, which can vary a lot.
- the invention proposes to modify the detection means present on the sensor.
- An intraoral oral radiological image sensor comprises a matrix of lines and columns of photosensitive pixels each comprising a photodiode and a transistor circuit for collecting the charges generated by the light in the pixel and converting them into voltage, with for each column of pixels a column driver common to all pixels of the column, the column driver being connected to a respective reading circuit for the column, and with an addressing circuit of lines for addressing the pixels of a selected line and reporting on the column conductors useful signals from the pixels of the selected line and representing the illumination of these pixels.
- the sensor according to the invention is characterized in that it comprises, in the middle of the matrix and in the place of a central column or a central line of pixels, a series of photodiodes all electrically connected in parallel with a side to a reference potential and on the other side to the same detection conductor extending along the series of photodiodes, this detection conductor being connected to a detection circuit providing a trigger signal for imaging when the detected current or the variation of this current exceeds a threshold showing that an X-ray flash has started.
- the senor has a generally rectangular shape
- the series of photodiodes is put in the place of a column or a line oriented in the direction of the length.
- the columns in the direction of the collection of signals
- the series of photodiodes used to detect an X-ray flash and the detection conductor then extend in the direction of the column conductors which collect the useful signals.
- the photodiodes are preferably distributed at the same pitch as the pixels in the columns or rows of pixels that surround it. These photodiodes are preferably technologically identical to the photodiodes of the pixels and they preferably have the same dimensions.
- FIG. 1 represents a general view of a dental radiological sensor of the prior art
- FIG. 2 represents the general organization of the matrix of pixels in an embodiment of the prior art
- FIG. 3 represents the general organization of the matrix of pixels in a dental radiological sensor according to the invention
- FIG. 4 represents an electrical diagram corresponding to the architecture of the sensor according to the invention.
- FIG. 5 represents an example of organization of the matrix with several series of column detection photodiodes
- FIG. 6 represents an example of organization with a column and a line of detection photodiodes
- FIG. 7 represents an example of organization with a series of columnar central photodiodes and sets of photodiodes on three different lines, each occupying only a portion of a line.
- FIG. 1 shows at scale 1 an intraoral dental radiological sensor 10 comprising a visible image sensor covered with a scintillator emitting visible light under the effect of X-rays, all enclosed in a housing whose dimensions (a few centimeters of side, a few millimeters thick) allow the introduction into the mouth of a patient.
- the sensor has an output cable 20 but wireless communication would also be possible between the sensor and a computer for collecting the electronic image.
- the visible image sensor is made of monocrystalline silicon, which is sensitive to the visible light emitted by the scintillator. It is constituted by a matrix of photosensitive pixels and control and read circuits, capable of triggering the acquisition of an electronic image and extracting from each pixel a useful signal representing the illumination of this pixel.
- the sensor housing may have a rectangular shape with cut corners as shown in Figure 1, and the integrated circuit chip on which are formed the matrix of pixels and the control circuits and
- the reading plate preferably has itself a rectangular shape with cut corners.
- Such an integrated circuit chip is shown in FIG. 2 and is designated by the reference CPT.
- the matrix of photosensitive pixels is designated by MPIX; it is composed of a regular arrangement with constant steps of columns of pixels and rows of pixels.
- the reference CPIX designates a column of pixels taken as example and hatched; similarly, the reference LPIX designates a line of pixels, taken by way of example and also hatched.
- the sequencing circuits which include control and reading circuits, are symbolized here in a very simplified manner by the representation:
- a line decoder LDEC on an elongated lateral edge of the chip or even on both edges, which serves to successively address the different lines of pixels by means of line conductors which each connect all the pixels of the same line,
- a reading circuit RD which serves to extract the useful signal from the pixels of an addressed line; this signal is collected by column conductors which connect all the pixels of the same column of pixels and it is directed by these conductors to the read circuit RD placed at the foot of the matrix.
- PLT output pads of the integrated circuit chip make it possible to provide on the outside of the chip analog or digital electronic signals representing the electronic image resulting from exposure to X-rays.
- the columns are generally oriented in the direction of the length while the lines are oriented in the direction of the width, but it is not obligatory.
- Figure 3 shows the organization of a sensor according to the invention.
- a column of pixels has been replaced by a series SPHx of detection photodiodes, all connected to the same detection conductor CD which extends along the replaced column which is connected to a DX detection circuit located at the foot of the matrix.
- FIG. 1 shows the organization of a sensor according to the invention.
- the matrix is composed of pixels distributed regularly with a certain pitch along the lines and each represented by a hatched square, each pixel comprising a photodiode and a few transistors; a central column of the matrix is replaced by simple photodiodes, each represented by a circle, and these photodiodes are all directly connected to the common detection conductor CD, itself connected to the detection circuit DX.
- the pitch of the matrix is preserved, in that the series of photodiodes occupies a maximum width equal to the pitch of the pixels.
- the detection photodiodes of this series are distributed in the direction of the columns with the same column step as the pixels.
- the steps in line and in column are in principle identical.
- the series of photodiodes extends over all or almost all of the height of the pixel array.
- the photodiodes are identical in all points (technology and dimensions) to the photodiodes that are present in the active pixels.
- FIG. 4 represents the electrical diagram corresponding to this organization, in an example in which each pixel comprises a photodiode PH and three MOS transistors which are a transistor Trs of periodic reset of the photodiode at the beginning of integration, a read transistor TL mounted voltage follower for copying on its source the potential present on its gate, and a line selection transistor TS controlled by a line driver (not shown) connected to all TS transistors of a line controlled by the decoder of line.
- the selection transistor connects, when made conductive, the read transistor to a DC column conductor.
- the sequencing circuits for acquiring an electronic image at the time of an X-ray flash are not shown in FIG. 4; they control the reset transistors and the line select transistors.
- the pixel could comprise a fourth transistor or transfer transistor when the pixel is constituted with a node of intermediate storage isolated from the photodiode by this transistor.
- the reset transistor then serves to reset the storage node.
- a fifth transistor may be provided to separately reset the photodiode and the intermediate storage node.
- the detection photodiodes of the SPHx series are each housed in the space reserved for a pixel, but this space does not include transistors (or, if it has them for reasons of simplification of the patterning patterns of the matrix, these transistors are not controlled like those of the pixels of the matrix and in particular they are not connected to the line decoder).
- These photodiodes PHx are all connected to the ground, that is to say to a reference potential to which are connected all the photodiodes PH of the pixels, and they are all directly connected (that is to say without interposition of a controllable transistor) to the column conductor CD.
- the line decoder is therefore not used for addressing the PHx photodiodes since they are systematically connected to the conductor CD and continuously supply the latter with the current they generate under the effect of light in the presence of an X-ray flash or the inevitable dark current that they generate in the absence of X-rays.
- the detection circuit DX has an input connected to the detection conductor CD.
- This circuit can have a very simple threshold comparator function and it provides an output signal to the general sequencer of the pixel matrix to allow the triggering of a full image capture when the current received by the detector exceeds a threshold determined.
- the current threshold can be a fixed threshold or a threshold adapted automatically according to the conditions of the environment (in particular according to the temperature conditions).
- the threshold is chosen with a value sufficient not to cause tripping under the effect of the dark current of the series of photodiodes when the latter increases as a result of an increase in temperature.
- an automatically adapted threshold several solutions can be provided. For example, it can be provided that a variable threshold is generated by a temperature sensitive circuit, the threshold increasing with temperature.
- the threshold may be set to a certain value above an average of the dark current received on the conductor prior to X-ray exposure; thus, only a sudden jump in current, due to an X-ray flash, will cause the threshold to be exceeded and will trigger image capture.
- the threshold is defined as a differential between two successive instants, the threshold being a slope threshold of growth of the current received.
- the current is converted into voltage by a simple current-voltage conversion circuit such as a capacitive transimpedance amplifier (CTIA), and it is this voltage that is observed, in absolute value. or in variation, to produce the electronic imaging authorization signal.
- CTIA capacitive transimpedance amplifier
- a simple threshold voltage comparator will be used in the simplest case.
- the series of detection photodiodes PHx placed in the middle of the matrix and in the meaning of the greater length of the rectangular sensor has the very important advantage of generally receiving a larger dose of X-rays (ie light generated by X-rays but we will speak more simply and for convenience of X-ray dose) than photodiodes that would be placed on the side of the pixel array, because when the sensor is in the mouth, it is placed so that its center line in the direction of the length is very little masked by the patient's teeth or jaw.
- the sensor when the desired image is an image taken with the mouth almost closed, while the patient bites a sensor support, the sensor is placed on the support so that the median line in the direction of the length is arranged along the support. Since the support is X-ray transparent, it passes a dose of X-rays directly on the series of photodiodes aligned along the median line of the X-ray. sensor. Therefore, even in this particular case of the closed mouth, the series of photodiodes is particularly well exposed to X-rays.
- the series of photodiodes occupies only the width of a column of pixels, it does not interfere very little with the final electronic image.
- the pixels may have a size of 20 micrometers by 20 micrometers, while the details useful to the practitioner for his diagnosis rarely have a dimension less than 100 micrometers per 100 micrometers.
- the luminance value of the missing pixel in each line is reconstructed by interpolation between the two neighboring pixels of the same line and this is very easy since all the missing pixels are located at the same median position in the different lines.
- the large number (several hundred) of PHx detection photodiodes present in the series makes it possible to obtain a sufficient detection current without it being necessary to provide that the detection photodiodes have a surface greater than one pixel.
- the detection circuit DX will in principle be placed at the bottom of the matrix of pixels, with the read circuits RD of the matrix. It has been shown in FIG. 3 as being located below the RD readout circuits, but it is not mandatory. Its location depends in particular on its size, which is greater or smaller depending on the embodiment envisaged, and according to the desired functionalities (detection of occurrence of flash X, detection of dose received for stopping the shooting of image, triggering d 'flash stop).
- the production of the photodiode series is very easy since the photodiodes are technologically identical to the photodiodes of the useful pixels of the matrix.
- the series of detection photodiodes and the detection conductor are crucially identical to the photodiodes of the useful pixels of the matrix.
- CDs can also be used to determine the end of the picture. Indeed, it is possible to integrate a signal representing the current received on the conductor CD; the integral of the current then represents an X-ray dose received by the series of photodiodes. This dose is representative of the dose received by the patient.
- An end of integration control circuit can therefore be connected to the CD conductor as the DX circuit to perform received dose detection and control the sequencing circuitry to complete the integration of electrical charges into the pixels.
- the series of photodiodes and the detection conductor can be used to stop the X-ray flash when the received dose has reached a predetermined value.
- An X flash stop control circuit must then be connected to the detection conductor CD, and this circuit transmits a stop signal to the X-ray source (for example by wire) when the received dose is sufficient.
- the flash stop control circuit X may be the same as the integration stop control circuit.
- the series of photodiodes placed in the middle of the matrix in the direction of the greatest length would replace a line of pixels. by occupying the width of this line.
- one or two other secondary series of photodiodes can be provided. aligned in the direction of the greatest length of the sensor parallel to the first series and each replacing a respective column (or row) of pixels.
- These other series of photodiodes are each connected to a conductor extending parallel to the series and connected to the detection conductor CD. The currents of these other series add to the current generated in the first series of photodiodes.
- FIG. 5 represents an example with two other series of photodiodes SPHx1 and SPHx2 replacing two other columns of pixels, respectively on either side of the central column SPHx.
- the image information is also reconstructed by interpolation of the signals provided by two pixels located on a line on either side of a detection photodiode.
- Figure 6 shows an example with a main series SPHx and a secondary series SPHy, perpendicular.
- the secondary series is placed on a median line of the matrix, but it could be placed on either side of this line; one can also have two series or three secondary series of photodiodes aligned in this direction.
- the luminance received by a missing pixel is interpolated by interpolation, but this time by interpolating the signals of two pixels placed in columns on either side of a given photodiode.
- This solution can be combined with that of FIG. 5 in which there are several series in columns in the direction of the length of the sensor. In all cases, the conductors of all the series are connected directly to the CD conductor of the main series SPHx which is oriented in the direction of the greatest length.
- Figure 7 shows that the series of photodiodes do not necessarily extend over the entire length or width of the pixel array.
- the series preferably depart from the central series to facilitate the connection between the different conductors corresponding to each series, but this is not mandatory, the connection can also be made from outside the matrix.
Abstract
Description
Claims
Priority Applications (3)
Application Number | Priority Date | Filing Date | Title |
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US15/547,095 US9907521B2 (en) | 2015-01-30 | 2016-01-15 | Radiation sensor with X-ray detection |
JP2017538207A JP6752801B2 (ja) | 2015-01-30 | 2016-01-15 | X線検出による放射線センサ |
CN201680007883.6A CN107257661B (zh) | 2015-01-30 | 2016-01-15 | 利用x射线检测的放射传感器 |
Applications Claiming Priority (2)
Application Number | Priority Date | Filing Date | Title |
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FR1550738A FR3032105B1 (fr) | 2015-01-30 | 2015-01-30 | Capteur radiologique avec detection de rayons x |
FR1550738 | 2015-01-30 |
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WO2016120091A1 true WO2016120091A1 (fr) | 2016-08-04 |
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PCT/EP2016/050730 WO2016120091A1 (fr) | 2015-01-30 | 2016-01-15 | Capteur radiologique avec detection de rayons x |
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US (1) | US9907521B2 (fr) |
JP (1) | JP6752801B2 (fr) |
CN (1) | CN107257661B (fr) |
FR (1) | FR3032105B1 (fr) |
WO (1) | WO2016120091A1 (fr) |
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US11134903B2 (en) * | 2018-10-16 | 2021-10-05 | Shayda Cullen | Digital dental x-ray sensor device having a rounded housing |
US10506992B1 (en) * | 2018-10-16 | 2019-12-17 | Shayda Cullen | Digital dental x-ray sensor device having a rounded housing |
US11191497B2 (en) * | 2018-10-16 | 2021-12-07 | Shayda Cullen | Digital dental x-ray sensor device having a rounded housing including a radio transceiver |
FR3094593B1 (fr) * | 2019-03-29 | 2021-02-19 | Teledyne E2V Semiconductors Sas | Procédé de synchronisation de données numériques envoyées en série |
FR3101768A1 (fr) * | 2019-10-10 | 2021-04-16 | Teledyne E2V Semiconductors Sas | Capteur d’image radiologique intra-oral a pixels actifs et procede de prise d’image associe |
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US20060193436A1 (en) * | 2002-10-03 | 2006-08-31 | Schick Technologies, Inc. | Intraoral image sensor |
US20070223649A1 (en) * | 2004-07-22 | 2007-09-27 | Christian De Godzinsky | Arrangement for intra-oral x-ray imaging |
FR2930841A1 (fr) * | 2008-04-30 | 2009-11-06 | E2V Semiconductors Soc Par Act | Capteur d'image a coins coupes avec un multiplexeur entre deux lignes adjacentes de pixels. |
FR2943179A1 (fr) * | 2009-03-13 | 2010-09-17 | E2V Semiconductors | Capteur d'image mos et procede de lecture avec transistor en regime de faible inversion. |
US20110013746A1 (en) * | 2008-10-27 | 2011-01-20 | Imaging Sciences International Llc | Triggering of intraoral x-ray sensor using pixel array sub-sampling |
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US5510623A (en) * | 1995-02-24 | 1996-04-23 | Loral Fairchild Corp. | Center readout intra-oral image sensor |
GB9515762D0 (en) * | 1995-08-01 | 1995-10-04 | Eev Ltd | Imaging apparatus |
GB0514998D0 (en) * | 2005-07-21 | 2005-08-31 | E2V Tech Uk Ltd | Sensor with trigger pixels for imaging of pulsed radiation |
FR2959901B1 (fr) * | 2010-05-04 | 2015-07-24 | E2V Semiconductors | Capteur d'image a matrice d'echantillonneurs |
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2015
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- 2016-01-15 JP JP2017538207A patent/JP6752801B2/ja active Active
- 2016-01-15 US US15/547,095 patent/US9907521B2/en active Active
- 2016-01-15 CN CN201680007883.6A patent/CN107257661B/zh active Active
- 2016-01-15 WO PCT/EP2016/050730 patent/WO2016120091A1/fr active Application Filing
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US20060193436A1 (en) * | 2002-10-03 | 2006-08-31 | Schick Technologies, Inc. | Intraoral image sensor |
US20070223649A1 (en) * | 2004-07-22 | 2007-09-27 | Christian De Godzinsky | Arrangement for intra-oral x-ray imaging |
FR2930841A1 (fr) * | 2008-04-30 | 2009-11-06 | E2V Semiconductors Soc Par Act | Capteur d'image a coins coupes avec un multiplexeur entre deux lignes adjacentes de pixels. |
US20110013746A1 (en) * | 2008-10-27 | 2011-01-20 | Imaging Sciences International Llc | Triggering of intraoral x-ray sensor using pixel array sub-sampling |
FR2943179A1 (fr) * | 2009-03-13 | 2010-09-17 | E2V Semiconductors | Capteur d'image mos et procede de lecture avec transistor en regime de faible inversion. |
Also Published As
Publication number | Publication date |
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JP6752801B2 (ja) | 2020-09-09 |
US20180008214A1 (en) | 2018-01-11 |
FR3032105A1 (fr) | 2016-08-05 |
FR3032105B1 (fr) | 2017-01-27 |
JP2018510671A (ja) | 2018-04-19 |
US9907521B2 (en) | 2018-03-06 |
CN107257661A (zh) | 2017-10-17 |
CN107257661B (zh) | 2020-10-30 |
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