US20010028701A1 - X-ray diagnostic installation having an X-ray image converter with combined back light/dose measuring unit - Google Patents
X-ray diagnostic installation having an X-ray image converter with combined back light/dose measuring unit Download PDFInfo
- Publication number
- US20010028701A1 US20010028701A1 US09/819,251 US81925101A US2001028701A1 US 20010028701 A1 US20010028701 A1 US 20010028701A1 US 81925101 A US81925101 A US 81925101A US 2001028701 A1 US2001028701 A1 US 2001028701A1
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- US
- United States
- Prior art keywords
- light
- ray
- image converter
- measuring unit
- ray image
- Prior art date
- Legal status (The legal status is an assumption and is not a legal conclusion. Google has not performed a legal analysis and makes no representation as to the accuracy of the status listed.)
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Classifications
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- 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
- G01T1/20188—Auxiliary details, e.g. casings or cooling
- G01T1/2019—Shielding against direct hits
-
- H—ELECTRICITY
- H05—ELECTRIC TECHNIQUES NOT OTHERWISE PROVIDED FOR
- H05G—X-RAY TECHNIQUE
- H05G1/00—X-ray apparatus involving X-ray tubes; Circuits therefor
- H05G1/08—Electrical details
- H05G1/64—Circuit arrangements for X-ray apparatus incorporating image intensifiers
Definitions
- the present invention is directed to an X-ray diagnostic installation of the type having a high-voltage generator for an X-ray tube for generating an X-ray beam, an X-ray image converter that has a scintillator layer and a semiconductor layer with light-sensitive pixel elements arranged in a matrix, and a combined back light/dose measuring unit arranged therebehind in the beam direction that is formed by an array of light-emitting diodes arranged in a matrix, as backside illumination and light-sensitive sensors that acquire the X-ray dose, as sensors, with a measurement transducer for the control of the high-voltage generator being connected thereto.
- German OS 196 06 873 discloses an X-ray diagnostic installation of this type shown in FIGS. 1 and 2 having an X-ray tube 2 supplied with high voltage and filament voltage by a voltage generator 1 as an X-ray unit that generates a cone-shaped beam of X-rays 3 that penetrates a patient and is incident as an X-ray image on a two-dimensional X-ray image converter 5 that is sensitive to X-rays 3 .
- the X-rays are incident thereon attenuated according to the transparency of the patient 4 .
- the X-ray image converter 5 converts the X-ray image into electrical signals that are supplied to an image system 7 as digital image data 6 .
- the image system 7 can include a calculating circuit, filter circuits, converters, image memories and processing circuits, these not being shown.
- a monitor 8 For playback of the acquired X-ray images, it is connected to a monitor 8 .
- Control elements 9 are connected to the remaining components of the X-ray diagnostic installation via a system controller and communication 10 .
- the system controller and communication 10 also has at least one measurement transducer that is connected to the voltage generator 1 for controlling the X-ray dose.
- FIG. 2 shows the known X-ray image converter 5 of FIG. 1 in greater detail. It has a scintillator 11 onto which the X-rays 3 are incident, these being converted into a visible X-ray image according to the attenuation by the patient 4 .
- the scintillator 11 can be composed of cesium iodide (Csl).
- the visible light 12 generated by the scintillator 11 is incident onto a number of light-sensitive pixel elements, for example photodiodes 13 , that are arranged on a glass substrate 14 arranged in a pixel matrix.
- the semiconductor of the pixel matrix can, for example, be composed of hydrogen-doped amorphous silicon (aSi:H).
- the measured signals 19 of the photodiodes 17 can be used for dose control. To that end, the current is integrated up to the dose D(t x ) at time t x D ⁇ ( t x ) ⁇ ⁇ 0 t x ⁇ I ⁇ ( t ) ⁇ ⁇ t
- the X-rays 3 are turned off at time t x , when the desired accumulated dose has been reached.
- the photodiodes 17 of the combined back light/dose measuring unit 15 are arranged in the same plane as the light-emitting diodes 16 and, thus, parallel to the X-ray image converter 5 , they are also exposed to the X-radiation, so that errors in the dose measurement can occur. Further, all photodiodes cannot be employed since some are not resistant to X-radiation.
- German OS 44 05 233 discloses an X-ray image device wherein a planar image converter is coupled to a luminescent screen via an optical coupling means. Further, the natural lateral light scatter of the luminescent screen is utilized by placing a light sensor of an automatic exposure unit at the narrow side.
- This object is inventively achieved in that light waveguides are arranged in front of the light-sensitive sensors of the combined back light/dose measuring unit, the light waveguides conducting the light that proceeds from the X-ray image converter during the irradiation and that is incident onto the combined back light/dose measuring unit onto the light-sensitive sensors.
- the light-sensitive sensors can be shielded against X-rays by a covering and/or can be arranged outside the X-rays.
- the homogeneity of the back side light can be improved when a diffusor layer is arranged between X-ray image converter and back light/dose measuring unit.
- the precision of the measurement in the central region can be enhanced when the light entry faces of the light waveguides are arranged more densely in the center of the back light/dose measuring unit.
- the structural outlay given high precision of the measurement can be simplified when a number of light waveguides are respectively allocated to one of the photodiodes.
- FIG. 2 shows structure of a known X-ray image converter.
- FIG. 3 shows an exemplary structure of the inventive X-ray image converter.
- FIG. 5 illustrates another inventive arrangement of the pixel elements of the combined back light/dose measuring unit.
- light waveguides 20 are provided between the light-emitting diodes 16 instead of the photodiodes, these light waveguides 20 redirecting the incident light onto light-sensitive sensors, for example photodiodes 17 , that are arranged at other locations, for example at the edge of the back light/dose measuring unit 15 .
- These locations for example, can lie outside the X-rays 3 , can be shielded from the X-rays 3 by a covering of, for example, lead or can offer other design advantages.
- the light entry faces of the light waveguides 20 can be smaller than the surfaces of the light-emitting diodes 16 , so that a large interspace that influences the homogeneity of the backside illumination does not exist.
- Several or even all light waveguides 20 can be combined onto a photodiode 17 .
- the individual measured signals 19 of the photodiodes 17 allocated to the individual light entry faces 22 can be combined into groups for forming regions referred to as dominants, by connecting a number of photodiodes 17 to one measurement transducer. As a result, larger areas are obtained; only the mean dose thereof is to be interpreted. A number of light waveguides 20 , however, can already be conducted onto one of the photodiodes 17 , so that a fixed allocation of the regions required for the dose measurement is established and a region selection ensues only via the selection of the photodiodes 17 .
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- Physics & Mathematics (AREA)
- Health & Medical Sciences (AREA)
- Life Sciences & Earth Sciences (AREA)
- General Physics & Mathematics (AREA)
- High Energy & Nuclear Physics (AREA)
- Molecular Biology (AREA)
- Spectroscopy & Molecular Physics (AREA)
- Measurement Of Radiation (AREA)
- Apparatus For Radiation Diagnosis (AREA)
Abstract
Description
- 1. Field of the Invention
- The present invention is directed to an X-ray diagnostic installation of the type having a high-voltage generator for an X-ray tube for generating an X-ray beam, an X-ray image converter that has a scintillator layer and a semiconductor layer with light-sensitive pixel elements arranged in a matrix, and a combined back light/dose measuring unit arranged therebehind in the beam direction that is formed by an array of light-emitting diodes arranged in a matrix, as backside illumination and light-sensitive sensors that acquire the X-ray dose, as sensors, with a measurement transducer for the control of the high-voltage generator being connected thereto.
- 2. Description of the Prior Art
- German OS 196 06 873 discloses an X-ray diagnostic installation of this type shown in FIGS. 1 and 2 having an
X-ray tube 2 supplied with high voltage and filament voltage by a voltage generator 1 as an X-ray unit that generates a cone-shaped beam ofX-rays 3 that penetrates a patient and is incident as an X-ray image on a two-dimensionalX-ray image converter 5 that is sensitive toX-rays 3. The X-rays are incident thereon attenuated according to the transparency of the patient 4. TheX-ray image converter 5 converts the X-ray image into electrical signals that are supplied to animage system 7 asdigital image data 6. In a known way, theimage system 7 can include a calculating circuit, filter circuits, converters, image memories and processing circuits, these not being shown. For playback of the acquired X-ray images, it is connected to amonitor 8.Control elements 9 are connected to the remaining components of the X-ray diagnostic installation via a system controller andcommunication 10. The system controller andcommunication 10 also has at least one measurement transducer that is connected to the voltage generator 1 for controlling the X-ray dose. - FIG. 2 shows the known
X-ray image converter 5 of FIG. 1 in greater detail. It has ascintillator 11 onto which theX-rays 3 are incident, these being converted into a visible X-ray image according to the attenuation by the patient 4. Thescintillator 11 can be composed of cesium iodide (Csl). Thevisible light 12 generated by thescintillator 11 is incident onto a number of light-sensitive pixel elements, forexample photodiodes 13, that are arranged on aglass substrate 14 arranged in a pixel matrix. The semiconductor of the pixel matrix can, for example, be composed of hydrogen-doped amorphous silicon (aSi:H). - As combined back light/
dose measuring unit 15, an array of light-emitting diodes 16 andphotodiodes 17 is arranged behind theX-ray image converter 5 as seen in the direction of theX-rays 3 for resetting residual charges of the pixel elements due to illumination of the semiconductor of theX-ray image converter 5, given simultaneous measurement of the dose power or dose. - The light-
emitting diodes 16 of the back light/dose measuring unit 15 generate anoptical backside light 18 in order to improve the temporal signal behavior of theX-ray image converter 5. A resetting by illumination of the pixel matrix of thephotodiodes 13 of theX-ray image converter 5 ensues between two readout events. As a result, these are completely discharged and low-impedance for speed-up. Since the illumination cannot ensue line-by-line, a simultaneous, common resetting of the entire array is undertaken. - Approximately 15% of the
scintillator light 12 converted by the scintillator penetrates the semiconductor layer of thepixel matrix 13 and theglass substrate 14. This light intensity, which is a criterion for the incident dose power, is measured for the purpose of dose control. To this end, the combined back light/dose measuring unit 15 is composed ofsmall photodiodes 15 arranged between light-emitting diodes 16 that are respectively connected to measurement transducers via switches for the selection of an arbitrary dominant in order to thus measure the X-ray dose. With the X-ray irradiation as a criterion for the accumulating X-ray dose, the ongoing radiation can be shut off by the automatic exposure unit after a prescribed value has been reached. - The electrical measured
signals 19 that thephotodiodes 17 generate are a criterion for the dose power or dose. The current I(t) is thereby a criterion for the dose power DL(t). -
- The
X-rays 3 are turned off at time tx, when the desired accumulated dose has been reached. - Since the
photodiodes 17 of the combined back light/dose measuring unit 15 are arranged in the same plane as the light-emitting diodes 16 and, thus, parallel to theX-ray image converter 5, they are also exposed to the X-radiation, so that errors in the dose measurement can occur. Further, all photodiodes cannot be employed since some are not resistant to X-radiation. - German OS 44 05 233 discloses an X-ray image device wherein a planar image converter is coupled to a luminescent screen via an optical coupling means. Further, the natural lateral light scatter of the luminescent screen is utilized by placing a light sensor of an automatic exposure unit at the narrow side.
- The lateral light propagation of the luminescent screen, however, must always be minimized because of the spatial resolution, i.e. light from the central regions of interest hardly proceeds to the sensor. Further, only an integral, edge-emphasized but not a spatially resolved light measurement is possible.
- An object of the present invention is to provide an X-ray diagnostic installation of the type initially described that enables a simple, fast and reliable acquisition of the X-ray dose during the irradiation with X-rays in A spatially resolved fashion, but wherein the light-sensitive pixel elements are not charged with X-rays for measurement.
- This object is inventively achieved in that light waveguides are arranged in front of the light-sensitive sensors of the combined back light/dose measuring unit, the light waveguides conducting the light that proceeds from the X-ray image converter during the irradiation and that is incident onto the combined back light/dose measuring unit onto the light-sensitive sensors.
- Inventively, the light-sensitive sensors can be shielded against X-rays by a covering and/or can be arranged outside the X-rays.
- The homogeneity of the back side light can be improved when a diffusor layer is arranged between X-ray image converter and back light/dose measuring unit.
- The precision of the measurement in the central region can be enhanced when the light entry faces of the light waveguides are arranged more densely in the center of the back light/dose measuring unit.
- It has proven advantageous when the X-ray image converter is an aSi:H detector.
- The measurement can ensue in arbitrary regions when the measured signals of the individual photodiodes are combined into groups to regions referred to as dominants.
- The structural outlay given high precision of the measurement can be simplified when a number of light waveguides are respectively allocated to one of the photodiodes.
- The light entry faces can have a uniform or non-uniform distribution, with the density of the light entry faces being higher in the middle and/or the dominant given a non-uniform distribution.
- It has proven expedient in view of a compact structure for a combined back light/dose measuring unit for an X-ray diagnostic installation with light-emitting diodes as backside illumination and light-sensitive sensors as detector of the X-ray dose when the light entry faces of the light waveguides are arranged between the light-emitting diodes of the array, with the light waveguides being brought together at one side in a narrow arc toward the back and behind the array, and with the light-sensitive sensors being arranged in a matrix and being coupled to the light waveguides laterally and outside the region of the array.
- FIG. 1 shows a known X-ray diagnostic installation with X-ray image converter.
- FIG. 2 shows structure of a known X-ray image converter.
- FIG. 3 shows an exemplary structure of the inventive X-ray image converter.
- FIG. 4 illustrates arrangement of the pixel elements of the inventive combined back light/dose measuring unit.
- FIG. 5 illustrates another inventive arrangement of the pixel elements of the combined back light/dose measuring unit.
- FIG. 6 shows another inventive structure of the X-ray image converter.
- Given the inventive exemplary embodiment shown in FIG. 3,
light waveguides 20 are provided between the light-emitting diodes 16 instead of the photodiodes, theselight waveguides 20 redirecting the incident light onto light-sensitive sensors, forexample photodiodes 17, that are arranged at other locations, for example at the edge of the back light/dose measuring unit 15. These locations, for example, can lie outside theX-rays 3, can be shielded from theX-rays 3 by a covering of, for example, lead or can offer other design advantages. - This arrangement wherein the light entry faces of the
light waveguides 20 and the light-emitting diodes 16 lie in one plane achieves the desirable result that the scintillator light 12 incident onto the combined back light/dose measuring unit 15 is directed onto the light-sensitive sensors, thephotodiodes 17, arranged outside the beam path. The light entry faces of thelight waveguides 20 can be smaller than the surfaces of the light-emittingdiodes 16, so that a large interspace that influences the homogeneity of the backside illumination does not exist. Several or even alllight waveguides 20 can be combined onto aphotodiode 17. - FIG. 4 schematically shows the active side of the back light/
dose measuring unit 15, whereby the light entry faces 22 of thelight waveguides 20 and light-emittingsurfaces 23 of the light-emitting diodes 16 are arranged mosaic-like. The light entry faces 22 cover less than 50% of the total area. They can have a uniform distribution, as shown in FIG. 4, however, the distribution alternatively can be non-uniform, in which case the density of thelight entry faces 22 is higher in the middle and/or the dominant. - The individual measured
signals 19 of thephotodiodes 17 allocated to the individual light entry faces 22 can be combined into groups for forming regions referred to as dominants, by connecting a number ofphotodiodes 17 to one measurement transducer. As a result, larger areas are obtained; only the mean dose thereof is to be interpreted. A number oflight waveguides 20, however, can already be conducted onto one of thephotodiodes 17, so that a fixed allocation of the regions required for the dose measurement is established and a region selection ensues only via the selection of thephotodiodes 17. - As indicated in FIG. 6, the
backside light 18 does not entirely uniformly illuminate theglass substrate 14 with the light-sensitive pixels 13 due to superimposition of the individual, divergent light beams. - For further improvement of the homogeneity in the illumination of the
glass substrate 14, adiffusor layer 24 can be attached betweenX-ray image converter 5 and back light/dose measuring unit. - Although modifications and changes may be suggested by those skilled in the art, it is the intention of the inventor to embody within the patent warranted hereon all changes and modifications as reasonably and properly come within the scope of his contribution to the art.
Claims (11)
Applications Claiming Priority (3)
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DE10015264.3 | 2000-03-28 | ||
DE10015264 | 2000-03-28 | ||
DE10015264A DE10015264C2 (en) | 2000-03-28 | 2000-03-28 | X-ray diagnostic device with an X-ray image converter with a combined rear light dose measuring unit |
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US20010028701A1 true US20010028701A1 (en) | 2001-10-11 |
US6359966B2 US6359966B2 (en) | 2002-03-19 |
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US09/819,251 Expired - Lifetime US6359966B2 (en) | 2000-03-28 | 2001-03-27 | X-ray diagnostic installation having an X-ray image converter with combined back light/dose measuring unit |
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US (1) | US6359966B2 (en) |
JP (1) | JP2001311778A (en) |
DE (1) | DE10015264C2 (en) |
Cited By (8)
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EP1388740A2 (en) | 2002-08-09 | 2004-02-11 | Canon Kabushiki Kaisha | Radiation imaging method and apparatus |
US20040223587A1 (en) * | 2003-04-24 | 2004-11-11 | Osamu Tsujii | Radiographic apparatus |
US20040227090A1 (en) * | 2003-05-15 | 2004-11-18 | Fuji Photo Film Co., Ltd. | Dosimetry system |
US20060237656A1 (en) * | 2002-08-27 | 2006-10-26 | Canon Kabushiki Kaisha | Image sensing apparatus and method using radiation |
US20080121808A1 (en) * | 2006-11-24 | 2008-05-29 | Tower Semiconductor Ltd. | High Resolution Integrated X-Ray CMOS Image Sensor |
US8292856B2 (en) | 2004-07-20 | 2012-10-23 | Medtronic, Inc. | Implantable cerebral spinal fluid drainage system |
US8981304B2 (en) | 2010-01-25 | 2015-03-17 | Fujifilm Corporation | Radiation detector |
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DE10241189A1 (en) * | 2002-09-05 | 2004-03-25 | Siemens Ag | Medical X-ray diagnostic instrument for recording both conventional X-ray images and sectional images has a fixed X-ray source and a source fixed to the C-frame, together with a single X-ray detector |
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US20050049879A1 (en) * | 2003-08-28 | 2005-03-03 | Alcatel | Communication device capable of interworking between voice communications and text communications |
JP5507202B2 (en) * | 2009-10-28 | 2014-05-28 | 富士フイルム株式会社 | Radiation imaging apparatus and radiation imaging system using the same |
KR101042046B1 (en) | 2010-05-31 | 2011-06-16 | 주식회사 디알텍 | Digital x-ray detector and method for initializing therefor |
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EP0233495B1 (en) * | 1986-01-21 | 1991-03-27 | Fuji Photo Film Co., Ltd. | Radiation image read-out apparatus |
GB9219727D0 (en) * | 1992-09-18 | 1992-10-28 | British Nuclear Fuels Plc | An inspection system |
DE4405233C1 (en) * | 1994-02-18 | 1995-05-04 | Siemens Ag | X-ray display unit |
US5568532A (en) * | 1994-08-12 | 1996-10-22 | Southeastern Universities Research Association, Inc. | Examination system utilizing ionizing radiation and a flexible, miniature radiation detector probe |
DE19606873C2 (en) | 1996-02-23 | 2000-10-12 | Siemens Ag | X-ray diagnostic device with a solid-state image converter |
US6271510B1 (en) * | 1998-12-18 | 2001-08-07 | Izzie Boxen | Fiber optic gamma camera having scintillating fibers |
-
2000
- 2000-03-28 DE DE10015264A patent/DE10015264C2/en not_active Expired - Fee Related
-
2001
- 2001-03-26 JP JP2001088713A patent/JP2001311778A/en not_active Abandoned
- 2001-03-27 US US09/819,251 patent/US6359966B2/en not_active Expired - Lifetime
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Also Published As
Publication number | Publication date |
---|---|
US6359966B2 (en) | 2002-03-19 |
DE10015264A1 (en) | 2001-10-11 |
JP2001311778A (en) | 2001-11-09 |
DE10015264C2 (en) | 2002-06-13 |
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