CA1190980A - Slit radiography - Google Patents
Slit radiographyInfo
- Publication number
- CA1190980A CA1190980A CA000418650A CA418650A CA1190980A CA 1190980 A CA1190980 A CA 1190980A CA 000418650 A CA000418650 A CA 000418650A CA 418650 A CA418650 A CA 418650A CA 1190980 A CA1190980 A CA 1190980A
- Authority
- CA
- Canada
- Prior art keywords
- slit
- image
- ray
- disposed
- collimator
- 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.)
- Expired
Links
Classifications
-
- 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
- G21K1/025—Arrangements for handling particles or ionising radiation, e.g. focusing or moderating using diaphragms, collimators using multiple collimators, e.g. Bucky screens; other devices for eliminating undesired or dispersed radiation
-
- 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
Abstract
ABSTRACT OF THE DISCLOSURE.
Improved slit radiography.
In radiography apparatus a moving slit colli-mator is disposed between an X-ray source and a patient undergoing examination. Radiation is detected with an X-ray image intensifier and television pickup chain.
The field of view of the television pickup is limited to that area of the output screen of the X-ray image intensifier which corresponds to the image produced by direct radiation which passes through the moving slit.
The view of the television pickup may be limited by a second slit, disposed between the X-ray image intensifier and television pickup which moves in synchronism with the first slit. Alternately, the view of a television pickup may be limited by synchronizing scan signals for the pickup of the with the motion of the slit collimator.
Improved slit radiography.
In radiography apparatus a moving slit colli-mator is disposed between an X-ray source and a patient undergoing examination. Radiation is detected with an X-ray image intensifier and television pickup chain.
The field of view of the television pickup is limited to that area of the output screen of the X-ray image intensifier which corresponds to the image produced by direct radiation which passes through the moving slit.
The view of the television pickup may be limited by a second slit, disposed between the X-ray image intensifier and television pickup which moves in synchronism with the first slit. Alternately, the view of a television pickup may be limited by synchronizing scan signals for the pickup of the with the motion of the slit collimator.
Description
,g~
P~ 21.0~ l 1.1l.1982 Improved slit radiography.
The :inven-t:ion r0la-tes to methods and apparatus for reducing the effects of glare, sca-tter, and off-~ocal radiation in the practice of slit radiography.
Background of -the invention.
Slit radiography has been knol~n for many years as a technique for reducing the background noise ~lich is generated by X-ray sca-tter during medica:L radiograplly.
In the prior art, a firs-t co:Llimator, which -typ:ica:L:Ly includes a long, narrow slit, :Ls disposed betwecn an X-ray source and a patient undergoing e~amination. ~
second corresponding slit :is disposed between the patient and an X-ray detector. Typically, -the X-ray de-tec-tor will comprise an X-ray sensitive phosphor screen, a sheet of X-ray film, or the input screen of an X-ray image inten-sifier tube. The sli-ts in the two collimators are moved in synchronisnn. The first slit assures that only a small area of the patien-t is illuminated with X-rays at any time. The second sli-t assures that only radiation which travels on a direc-t path from the X-ray source reaches the detector. The slits rnove to scan an entire field of view on the patient.
Background noise in a radiography system arises from three principal sources: direct X-ray scatter, image intensifier glare, and off-focal radiation. Scatter is principally X-rays produced in the patient by the Compton ef~ect but also includes some coherent (Rayleigh) sca-tter and some indirect photoelectric effect scatter. Sca-tter, together with photoelectric absorption, forms a conven-tional X-ray image by subtracting photons from a primar-y radiation beam at various points in the pa-tien-t.
In systems which utilize an X-ray image in-tensi-fier, an X-ray image is converted into an intensified Ll909~
P~ . o8~ 2 1.l1.1982 visible light image. The X-rays are first converted to lo~er energy photons in a scintillation layer at the input screen of the intensifier. The lower energy photons dif-f~se -to a photocathode where they produce an electron image, Tlle eLectrons are accelerated through an electron optical str~lctnre and strll~e a :fluorescent output screen where they are conver-tecl into vis:ible pllotons. Glare may be produced at each step: the X-rays may scatter in the input window and scintilla-tion layer of the tube; the low energy pho-tons may be scattered as they diffuse to -the photocathode;
the clectron image can undergo aberrations which contri-bnte to glare; and light produced :in the fluorescent ou-t-put screen can partially scatter or ref]ect before it; :is translll.tted out of the intenslfier.
X-ray radiation is usually produced in an X-ray tube as Bremsstrahlung or charac-teristic radiation from a ~eam of primary electrons which bombards a focal spot on a metal anode. The anode also elastically scatters some se-condary electrons. The tube electron optics are generally 20 llO t designed to focus secondary electrons and they usually stril~e the anode and generate X-rays far away from the focal spot of the primary electron beam. The tube thus comprises an e.Ytended source of radiation having a compli-cated configuration. Radiation from the focal spot can also 25 be scattered by the output window and filter in the port of the X-ray tube to produce off-focal radiation.
Summary of the invention.
In accordance with the invention, collima-ting means are provided between the output screen of an X-ray image intensifier and the output of a television pickup.
If a light collimator is used, this moves in synchronism with an X-ray collimator slit which is disposed between the X-ray source and the patient. The light collimator slit restricts the field of view of the television pickup to a limited area on the output screen of the image intensifier which corresponds to a portion of the image produced by direct radiation which reaches the inpu-t screen of the 98(~
PHA 21.0~8 3 1.11.1982 intensifier through the X-ray collimator slit. The light collimator prevents glare produced in the image intensi-fier tube from reaching the television pickup ancl contri-buting to background noise in the system and reduces the effects of off-focal rad:iation and scatter.
In a prefe:rred embodilllerlt of the invention, a collima-t:ion effect in the television picl~up means is achie~red by l:im:iting an area to be scanned in the tele-vision means to areas on a photosensitive face which corre-spond to a portion of the image which is formed by directradia-tion which passes through -the ~-ray collimator slit.
The scan is s~nchron:ized with the motion of the ~-ray collimator slit. The slit in the X-ray collimator may comprise a long rectangular opening which is aligned with its longitudinal dimension perpendicular to a linear mo-tion of -the collimator. In this case the plckup is elec-trically scanlled with a rectangular raster scan having horizontal lines parallel to the longitudinal dimension of the opening and a vertical scan which is synchronized with its motion. Alternatively, the X-ray collimator may be a disc with a sector shaped opening in which case the electrical scan of the pickup is in a polar geometry. The pickup may comprise a vidicon or o-ther vacuum tube tele-vision pickup or it may comprise a solid state array.
An additional synchronized X-ray collimator slit may be disposed between the patient and the input screen of the image intensifier to further reduce the effect of X-rays scattered in the patient. A further synchronized X-ray collimator slit may be provided at the output window of the X-ray source, between the source and the first X-ray collimator to reduce the background effects of off-focal radiation in the tube.
Brief description of the drawings.
The invention may be better understood by refe-rence to the attached drawings in which:
~igure 1 schematically represents an X-ray pick-up chain having rectangular slit collimators and .. , .. . _~_.. _ . ~ ~ ~.,.. .~ . . . ,~__., . .. , ~ ~ ~ . ,, . _ _ _. .___ _ , _ ____.. _ _. _._~.____ _ ~__ ._ __ _ ___ .....
9(~9~1 P~IA 21.08~ Ll 1.-l1.1982 Figure 2 schematically represents an X-ray pichup chain having sector-shaped disc collimators.
~e~cri tio~ of the referred embodiment.
- P e _ F:igure I is an ~-ray pickup cha:in ~hich incorpo-rates tlle improved sl:it radiography appa-ra-tus of the pre-sent invention. ,Y~ray radiation is genera-ted at the anode I0 of an ~-ray tube -I1 and e~ists the tube through an out-put window -I2 at the tube port -I3. Radiation from the tube is pro~jected through a pair of ~-ray collimators I4 and I~ (more partlcularly describcd belo~), through an e~aml.-ation area I6 ~hich includes a patient to be e.Yamined 17 tIlrougII a tIIird Y-ray coll:ima-tor 1~ and onto -the :input screen I9 of an ~-ray image intensif:ier tube 20. TIle ~-ray image inteIlsi~ier tuhe functions in a manner well known in tIIe ar-t to produce a visible image on an output window 21 ~iIIich corresponds to the X-ray image formed on the in-put ~indol~ 19. A television pickup 22, which may, :ror e~aIllple. comprise a vidicon tube or a solid state light detecting array, it is disposed to view the image on the output screen 21 through a light collimator 23. The tele-vision pickup 22 produces a video signal which may for e~ample, be displayed on a television monitor 24. The te-levision pickup 22 produces the video signal by sequenti-ally scanning image detecting elements which may, for e~ample, be in a ma-tri~ on the face of a vidicon -tube. The scan of the pickup is synchronized with the scan of the cathode ray tube of the television monitor 24; both scans being con-trolled by a sweep generator 25.
The collimators 14, 15, 18 and 23 comprise radi-ation-absorbing material (which in the case of ~-ray colli--mators 14, 15 and 1S may be lead and in the case of light collimator 23 may be metal or plastic) which defines a non-absorbing rectangular slit (14a, 15a~ 1~a and 23a) aligned with its longitudinal dimension perpendicular to the plane of the drawing in Figure 1. The collimators are movable in tlle vertical direction and are moved therein by motors 26, 2/, 2~ and 29 via drive mechanisms which are indicated ~ ~9~)9~1~
PHA 21.o~8 5 1.11.1982 schematically as dashed lines in which may, for e~ample, comprise racks and pinions. The motors are powered by a drive con-trol circuit 3O which maintains the sli-ts 1~a, 15a and l8a in alignmetl-t along a common line during their mot:ion. Sli-ts l5a and 1~a thus furlction in the mallner of prlor art sl:it rad:iography apparatus to limit direct ra-diation from -the source to a small portion of the input screen 19. The slit collimator 23 moves in synchronism with the motion of the slit collimators 14, 15 and 18, and is rnaintained in functional alignment therewith under con-trol of the drive control 3O, so -that it limits the field of view of the TV pickup 22 to a small area on the 01ltput screen 21 o~ the ~-ray image lntensi*ier which contains an image whlch corresponds to ~-ray intensity on the small area o~ the input screen whicll receives direct rad:iat:ion from the source througl1 the slits in collimators l~, 15 and 1~.
In a preferred embodiment of the invention, the vertical sweep produced by the sweep generator 25 and ap-plied -to the TV pickup 22 to read out image information is synchronized with the motion of the slit collimators so that the pickup tube is, at all times, producing an elec-trical output signal from light which is emi-tted from that portion of the output screen which images direct radiation through the slits. In a preferred embodiment, the sweep generator first scans a horizon-tal line on the face of the pickup tube immediately before light from the direct ra-diation area of the output screen 21 reaches the pickup.
The first sweep erases any information on the face of the tube which may be attributable to background radiation glare, scatter or off-focal radiation. Light from the output screen then produces a direct primary light image on -the swept area of the pickup tube and the sweep gene-rator produces a second horizontal line which reads out this information to the television monitor. The sequence is repeated for all lines in the T~ image.
In an alternate embodiment of the inven-tion.
ligh-t collimator 23 may be eliminated and -the sweep gene-PHA. 21.088 6 rator synchronized with the motion of X-ray collimators 14, 15 and 18.
Figure 2 illustrates an alternate embodiment of the radiography apparatus of Figure 1 wherein the colli-mators comprise rotating discs which are provided withsector shaped slit openings and which rotate in synchronism around a common axis. The axis may be disposed outside of the field of view of the X-ray image intensifier or may, advantageously be disposed within the field of view of the la image intensifier, that is: between the source and the input screen as illustrated in Figure 2. In that case the collimators 14, 15, 18 and 23 are most advantageously supported and driven at their peripheries by motors 26, 27, 28 and 29 under synchronous control from the drive 30.
The sweep of the pickup tube may also, in this embodiment, be synchronized with the motion of the collimator discs in which case the sweep of the pickup tube may be in a polar geometry of the type used in pulse position radar displays.
Further details of the construction of slit col-limators having rotating and scanning geometries are des-cribed in Rudin, S 'IFore-and Aft Rotating Aperture Wheel (RAW) Device for Improving Radiographic Contrast", Pro-ceedings SPIE Vol. 173 page 980~and Barnes G. T. in Brezovich, I.A., QThe Design and Performance of.a Scanning Multiple Slit Assembly", Med. Phys. 6, 197 (1979).
If the disc axis is located within the field of view of the ~-ray ima~e intensifier in the apparatus of Figure 2 there is a possibility that an artifact will be produced at the point on the image corresponding to the axis since, at some point, the width of the focal spot will exceed the width of the:aperture. If only one colli-mator is used, the rotation of the collimator will produce an average image. ~o~ever, a combination of two or more collimators will discriminate against radiation as the center of the collimator is approached. The artifact can be reduced if one of the collimators, for example, colli-8(~
PHA 21.088 7 1.11.1982 mator 15, is utilized as the beam defining device. Thiscan be acc.omplishecl by making the opening .in the beam de-fining collimator narrower than the openings in the re-mai.n:ing collilncltors and by enlarging the apertures in the o-thcr coll:imato.rs as :rc~qu:i:recd to alLow -the entire primary beam -to pass through.
P~ 21.0~ l 1.1l.1982 Improved slit radiography.
The :inven-t:ion r0la-tes to methods and apparatus for reducing the effects of glare, sca-tter, and off-~ocal radiation in the practice of slit radiography.
Background of -the invention.
Slit radiography has been knol~n for many years as a technique for reducing the background noise ~lich is generated by X-ray sca-tter during medica:L radiograplly.
In the prior art, a firs-t co:Llimator, which -typ:ica:L:Ly includes a long, narrow slit, :Ls disposed betwecn an X-ray source and a patient undergoing e~amination. ~
second corresponding slit :is disposed between the patient and an X-ray detector. Typically, -the X-ray de-tec-tor will comprise an X-ray sensitive phosphor screen, a sheet of X-ray film, or the input screen of an X-ray image inten-sifier tube. The sli-ts in the two collimators are moved in synchronisnn. The first slit assures that only a small area of the patien-t is illuminated with X-rays at any time. The second sli-t assures that only radiation which travels on a direc-t path from the X-ray source reaches the detector. The slits rnove to scan an entire field of view on the patient.
Background noise in a radiography system arises from three principal sources: direct X-ray scatter, image intensifier glare, and off-focal radiation. Scatter is principally X-rays produced in the patient by the Compton ef~ect but also includes some coherent (Rayleigh) sca-tter and some indirect photoelectric effect scatter. Sca-tter, together with photoelectric absorption, forms a conven-tional X-ray image by subtracting photons from a primar-y radiation beam at various points in the pa-tien-t.
In systems which utilize an X-ray image in-tensi-fier, an X-ray image is converted into an intensified Ll909~
P~ . o8~ 2 1.l1.1982 visible light image. The X-rays are first converted to lo~er energy photons in a scintillation layer at the input screen of the intensifier. The lower energy photons dif-f~se -to a photocathode where they produce an electron image, Tlle eLectrons are accelerated through an electron optical str~lctnre and strll~e a :fluorescent output screen where they are conver-tecl into vis:ible pllotons. Glare may be produced at each step: the X-rays may scatter in the input window and scintilla-tion layer of the tube; the low energy pho-tons may be scattered as they diffuse to -the photocathode;
the clectron image can undergo aberrations which contri-bnte to glare; and light produced :in the fluorescent ou-t-put screen can partially scatter or ref]ect before it; :is translll.tted out of the intenslfier.
X-ray radiation is usually produced in an X-ray tube as Bremsstrahlung or charac-teristic radiation from a ~eam of primary electrons which bombards a focal spot on a metal anode. The anode also elastically scatters some se-condary electrons. The tube electron optics are generally 20 llO t designed to focus secondary electrons and they usually stril~e the anode and generate X-rays far away from the focal spot of the primary electron beam. The tube thus comprises an e.Ytended source of radiation having a compli-cated configuration. Radiation from the focal spot can also 25 be scattered by the output window and filter in the port of the X-ray tube to produce off-focal radiation.
Summary of the invention.
In accordance with the invention, collima-ting means are provided between the output screen of an X-ray image intensifier and the output of a television pickup.
If a light collimator is used, this moves in synchronism with an X-ray collimator slit which is disposed between the X-ray source and the patient. The light collimator slit restricts the field of view of the television pickup to a limited area on the output screen of the image intensifier which corresponds to a portion of the image produced by direct radiation which reaches the inpu-t screen of the 98(~
PHA 21.0~8 3 1.11.1982 intensifier through the X-ray collimator slit. The light collimator prevents glare produced in the image intensi-fier tube from reaching the television pickup ancl contri-buting to background noise in the system and reduces the effects of off-focal rad:iation and scatter.
In a prefe:rred embodilllerlt of the invention, a collima-t:ion effect in the television picl~up means is achie~red by l:im:iting an area to be scanned in the tele-vision means to areas on a photosensitive face which corre-spond to a portion of the image which is formed by directradia-tion which passes through -the ~-ray collimator slit.
The scan is s~nchron:ized with the motion of the ~-ray collimator slit. The slit in the X-ray collimator may comprise a long rectangular opening which is aligned with its longitudinal dimension perpendicular to a linear mo-tion of -the collimator. In this case the plckup is elec-trically scanlled with a rectangular raster scan having horizontal lines parallel to the longitudinal dimension of the opening and a vertical scan which is synchronized with its motion. Alternatively, the X-ray collimator may be a disc with a sector shaped opening in which case the electrical scan of the pickup is in a polar geometry. The pickup may comprise a vidicon or o-ther vacuum tube tele-vision pickup or it may comprise a solid state array.
An additional synchronized X-ray collimator slit may be disposed between the patient and the input screen of the image intensifier to further reduce the effect of X-rays scattered in the patient. A further synchronized X-ray collimator slit may be provided at the output window of the X-ray source, between the source and the first X-ray collimator to reduce the background effects of off-focal radiation in the tube.
Brief description of the drawings.
The invention may be better understood by refe-rence to the attached drawings in which:
~igure 1 schematically represents an X-ray pick-up chain having rectangular slit collimators and .. , .. . _~_.. _ . ~ ~ ~.,.. .~ . . . ,~__., . .. , ~ ~ ~ . ,, . _ _ _. .___ _ , _ ____.. _ _. _._~.____ _ ~__ ._ __ _ ___ .....
9(~9~1 P~IA 21.08~ Ll 1.-l1.1982 Figure 2 schematically represents an X-ray pichup chain having sector-shaped disc collimators.
~e~cri tio~ of the referred embodiment.
- P e _ F:igure I is an ~-ray pickup cha:in ~hich incorpo-rates tlle improved sl:it radiography appa-ra-tus of the pre-sent invention. ,Y~ray radiation is genera-ted at the anode I0 of an ~-ray tube -I1 and e~ists the tube through an out-put window -I2 at the tube port -I3. Radiation from the tube is pro~jected through a pair of ~-ray collimators I4 and I~ (more partlcularly describcd belo~), through an e~aml.-ation area I6 ~hich includes a patient to be e.Yamined 17 tIlrougII a tIIird Y-ray coll:ima-tor 1~ and onto -the :input screen I9 of an ~-ray image intensif:ier tube 20. TIle ~-ray image inteIlsi~ier tuhe functions in a manner well known in tIIe ar-t to produce a visible image on an output window 21 ~iIIich corresponds to the X-ray image formed on the in-put ~indol~ 19. A television pickup 22, which may, :ror e~aIllple. comprise a vidicon tube or a solid state light detecting array, it is disposed to view the image on the output screen 21 through a light collimator 23. The tele-vision pickup 22 produces a video signal which may for e~ample, be displayed on a television monitor 24. The te-levision pickup 22 produces the video signal by sequenti-ally scanning image detecting elements which may, for e~ample, be in a ma-tri~ on the face of a vidicon -tube. The scan of the pickup is synchronized with the scan of the cathode ray tube of the television monitor 24; both scans being con-trolled by a sweep generator 25.
The collimators 14, 15, 18 and 23 comprise radi-ation-absorbing material (which in the case of ~-ray colli--mators 14, 15 and 1S may be lead and in the case of light collimator 23 may be metal or plastic) which defines a non-absorbing rectangular slit (14a, 15a~ 1~a and 23a) aligned with its longitudinal dimension perpendicular to the plane of the drawing in Figure 1. The collimators are movable in tlle vertical direction and are moved therein by motors 26, 2/, 2~ and 29 via drive mechanisms which are indicated ~ ~9~)9~1~
PHA 21.o~8 5 1.11.1982 schematically as dashed lines in which may, for e~ample, comprise racks and pinions. The motors are powered by a drive con-trol circuit 3O which maintains the sli-ts 1~a, 15a and l8a in alignmetl-t along a common line during their mot:ion. Sli-ts l5a and 1~a thus furlction in the mallner of prlor art sl:it rad:iography apparatus to limit direct ra-diation from -the source to a small portion of the input screen 19. The slit collimator 23 moves in synchronism with the motion of the slit collimators 14, 15 and 18, and is rnaintained in functional alignment therewith under con-trol of the drive control 3O, so -that it limits the field of view of the TV pickup 22 to a small area on the 01ltput screen 21 o~ the ~-ray image lntensi*ier which contains an image whlch corresponds to ~-ray intensity on the small area o~ the input screen whicll receives direct rad:iat:ion from the source througl1 the slits in collimators l~, 15 and 1~.
In a preferred embodiment of the invention, the vertical sweep produced by the sweep generator 25 and ap-plied -to the TV pickup 22 to read out image information is synchronized with the motion of the slit collimators so that the pickup tube is, at all times, producing an elec-trical output signal from light which is emi-tted from that portion of the output screen which images direct radiation through the slits. In a preferred embodiment, the sweep generator first scans a horizon-tal line on the face of the pickup tube immediately before light from the direct ra-diation area of the output screen 21 reaches the pickup.
The first sweep erases any information on the face of the tube which may be attributable to background radiation glare, scatter or off-focal radiation. Light from the output screen then produces a direct primary light image on -the swept area of the pickup tube and the sweep gene-rator produces a second horizontal line which reads out this information to the television monitor. The sequence is repeated for all lines in the T~ image.
In an alternate embodiment of the inven-tion.
ligh-t collimator 23 may be eliminated and -the sweep gene-PHA. 21.088 6 rator synchronized with the motion of X-ray collimators 14, 15 and 18.
Figure 2 illustrates an alternate embodiment of the radiography apparatus of Figure 1 wherein the colli-mators comprise rotating discs which are provided withsector shaped slit openings and which rotate in synchronism around a common axis. The axis may be disposed outside of the field of view of the X-ray image intensifier or may, advantageously be disposed within the field of view of the la image intensifier, that is: between the source and the input screen as illustrated in Figure 2. In that case the collimators 14, 15, 18 and 23 are most advantageously supported and driven at their peripheries by motors 26, 27, 28 and 29 under synchronous control from the drive 30.
The sweep of the pickup tube may also, in this embodiment, be synchronized with the motion of the collimator discs in which case the sweep of the pickup tube may be in a polar geometry of the type used in pulse position radar displays.
Further details of the construction of slit col-limators having rotating and scanning geometries are des-cribed in Rudin, S 'IFore-and Aft Rotating Aperture Wheel (RAW) Device for Improving Radiographic Contrast", Pro-ceedings SPIE Vol. 173 page 980~and Barnes G. T. in Brezovich, I.A., QThe Design and Performance of.a Scanning Multiple Slit Assembly", Med. Phys. 6, 197 (1979).
If the disc axis is located within the field of view of the ~-ray ima~e intensifier in the apparatus of Figure 2 there is a possibility that an artifact will be produced at the point on the image corresponding to the axis since, at some point, the width of the focal spot will exceed the width of the:aperture. If only one colli-mator is used, the rotation of the collimator will produce an average image. ~o~ever, a combination of two or more collimators will discriminate against radiation as the center of the collimator is approached. The artifact can be reduced if one of the collimators, for example, colli-8(~
PHA 21.088 7 1.11.1982 mator 15, is utilized as the beam defining device. Thiscan be acc.omplishecl by making the opening .in the beam de-fining collimator narrower than the openings in the re-mai.n:ing collilncltors and by enlarging the apertures in the o-thcr coll:imato.rs as :rc~qu:i:recd to alLow -the entire primary beam -to pass through.
Claims (10)
PROPERTY OR PRIVILEGE IS CLAIMED ARE DEFINED AS FOLLOWS:
1. In a radiography system which includes:
source means which function to direct X-ray rad-iation through an examination area;
an X-ray image intensifier having an input screen which is disposed to receive radiation from the source means which has passed through the examination area and an output screen for producing an intensified visible image which corresponds to radiation impinging on the input screen;
television pickup means disposed to view the out-put screen which function to produce a television signal corresponding to an image thereon; and first scanning means which define and move a first X-ray collimator slit system disposed between the source means and the examination area and which functions to limit direct radiation from the source means to a limited portion of the input screen; characterized in that second scanning means are provided which function, in syn-chronism with the motion of the first collimator system, to limit the view of the television pickup means to a limited area of the output screen on which the image cor-responds to radiation on the limited area of the input screen which receives direct radiation from the source means through the first slit.
source means which function to direct X-ray rad-iation through an examination area;
an X-ray image intensifier having an input screen which is disposed to receive radiation from the source means which has passed through the examination area and an output screen for producing an intensified visible image which corresponds to radiation impinging on the input screen;
television pickup means disposed to view the out-put screen which function to produce a television signal corresponding to an image thereon; and first scanning means which define and move a first X-ray collimator slit system disposed between the source means and the examination area and which functions to limit direct radiation from the source means to a limited portion of the input screen; characterized in that second scanning means are provided which function, in syn-chronism with the motion of the first collimator system, to limit the view of the television pickup means to a limited area of the output screen on which the image cor-responds to radiation on the limited area of the input screen which receives direct radiation from the source means through the first slit.
2. The apparatus of Claim 1, wherein: the second scanning means comprises a second diaphragm which defines a light collimator slit disposed between the output screen and the television pickup means and means for moving the second diaphragm so that the second slit is functionally aligned with and moves in synchronism with the first slit.
3. The apparatus of Claim 1 comprising means for scanning an image sensitive area of the television pickup means to produce a signal therefrom wherein the second scanning means functions to limit the scan of the image sensitive area to limited portions thereof corresponding with the said limited area of the output screen.
4. The apparatus of Claim 3, wherein the means for scanning the image sensitive area further function to discharge background image information from the limited portions of the image sensitive area before pro-ducing a signal which corresponds to an image produced by direct radiation.
5. The apparatus of Claim 4, wherein the televi-sion pickup means is a vidicon tube.
6. The apparatus of Claim 3, wherein the televi-sion pickup means is a solid state array.
7. The apparatus of Claim 2, wherein the first and second slits are sectors of circles disposed on a common axis and wherein the first and second scanning means function to rotate the first and second slits around a common axis.
8. The apparatus as claimed in Claim 1, 2 or 3, wherein the first collimating slit system comprises third diaphragm means which define a third collimator slit disposed between the examination area and the, input screen of the X-ray image intensifier means and means for moving the third diaphragm means so that the third slit is aligned with and moves in synchronism with a preceding slit of the system.
9. The apparatus as claimed in Claim 1, 2 or 3, wherein the first collimating slit system comprises fourth diaphragm means which define a fourth collimator slit disposed between the source means and a first slit of the first collimating system and means for moving the fourth diaphragm means so that the fourth slit is aligned with and moves in synchronism with the first slit.
10. The apparatus of Claim 3, wherein, the first slit is rectangular, the first scanning means moves the first diaphragm perpendicular to the longitudinal dimension of the first slit and wherein the means for scan-ning produces a raster scan having a horizontal sweep which is functionally parallel to the longitudinal dimen-sion of the first slit and a vertical sweep which is functionally parallel to the motion of the first slit.
Applications Claiming Priority (2)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| US06/337,031 US4404591A (en) | 1982-01-04 | 1982-01-04 | Slit radiography |
| US337,031 | 1982-01-04 |
Publications (1)
| Publication Number | Publication Date |
|---|---|
| CA1190980A true CA1190980A (en) | 1985-07-23 |
Family
ID=23318801
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| CA000418650A Expired CA1190980A (en) | 1982-01-04 | 1982-12-24 | Slit radiography |
Country Status (5)
| Country | Link |
|---|---|
| US (1) | US4404591A (en) |
| EP (1) | EP0083465B1 (en) |
| JP (1) | JPS58118733A (en) |
| CA (1) | CA1190980A (en) |
| DE (1) | DE3265470D1 (en) |
Families Citing this family (28)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US4493096A (en) * | 1982-12-17 | 1985-01-08 | General Electric Company | Method of X-ray imaging using slit scanning with controlled target erase |
| US4534051A (en) * | 1982-12-27 | 1985-08-06 | John K. Grady | Masked scanning X-ray apparatus |
| US4504859A (en) * | 1983-01-13 | 1985-03-12 | John K. Grady | Multiple X-ray image scanners |
| US4718076A (en) * | 1983-04-22 | 1988-01-05 | Kabushiki Kaisha Toshiba | X-ray imaging apparatus |
| IL69074A0 (en) * | 1983-06-26 | 1983-10-31 | Gur Optics & Systems Ltd | Systems and components for detecting electromagnetic radiation and displaying images produced thereby |
| NL8400845A (en) * | 1984-03-16 | 1985-10-16 | Optische Ind De Oude Delft Nv | DEVICE FOR GAP RADIOGRAPHY. |
| US4649559A (en) * | 1983-10-31 | 1987-03-10 | Xonics Imaging, Inc. | Digital radiography device |
| DE3345871A1 (en) * | 1983-12-19 | 1985-06-27 | Siemens AG, 1000 Berlin und 8000 München | X-RAY DIAGNOSTIC SYSTEM WITH AN IMAGE AMPLIFIER TELEVISION CHAIN AND INDIRECT CAMERA |
| NL8401411A (en) * | 1984-05-03 | 1985-12-02 | Optische Ind De Oude Delft Nv | DEVICE FOR GAP RADIOGRAPHY. |
| US4669105A (en) * | 1984-05-29 | 1987-05-26 | Aaron Fenster | System for quantitative arteriography |
| FR2565451B1 (en) * | 1984-05-30 | 1986-08-22 | Thomson Cgr | METHOD FOR MONITORING THE POSITION OF THE FIREPLACE OF A RADIOGENIC TUBE AND MONITORING DEVICE USING THE SAME |
| US4817123A (en) * | 1984-09-21 | 1989-03-28 | Picker International | Digital radiography detector resolution improvement |
| US4581753A (en) * | 1984-09-21 | 1986-04-08 | John K. Grady | Translatively driven X-ray aperture mask |
| US4896344A (en) * | 1984-10-15 | 1990-01-23 | Grady John K | X-ray video system |
| DE3500812A1 (en) * | 1985-01-11 | 1986-07-17 | Siemens AG, 1000 Berlin und 8000 München | X-RAY DIAGNOSTIC DEVICE WITH SEMI-TRANSPARENT PANEL |
| US4646339A (en) * | 1985-06-11 | 1987-02-24 | John K. Grady | Rotating X-ray mask with sector slits |
| US4696025A (en) * | 1986-06-02 | 1987-09-22 | University Of Toronto Innovations Foundation | Scanning apparatus |
| FR2621764A1 (en) * | 1987-10-13 | 1989-04-14 | Philips Massiot Mat Medic | Radiology apparatus equipped with a displaceable slotted screen under video synchronisation |
| US4947416A (en) * | 1988-10-21 | 1990-08-07 | General Electric Company | Scanning equalization radiography with stationary equalization detector |
| DE4005111A1 (en) * | 1990-02-17 | 1991-08-22 | Philips Patentverwaltung | X-RAY DIAGNOSTIC DEVICE WITH MEANS FOR THE ENLARGED VISUAL DISPLAY OF A SELECTABLE SECTION OF THE OVERALL IMAGE AREA |
| FR2803394B1 (en) * | 1999-12-30 | 2003-04-25 | Thomson Tubes Electroniques | X-RAY IMAGE DETECTION SYSTEM FOR SCANNING X-RAY GENERATOR |
| US6711235B2 (en) * | 2002-05-31 | 2004-03-23 | General Electric Cormpany | X-ray inspection apparatus and method |
| US20040120457A1 (en) * | 2002-12-20 | 2004-06-24 | University Of Massachusetts Medical Center | Scatter reducing device for imaging |
| US7388207B1 (en) | 2006-03-28 | 2008-06-17 | University Of Utah Research Foundation | Skew slit collimator and method of use thereof |
| CN102543242A (en) * | 2010-12-09 | 2012-07-04 | Ge医疗系统环球技术有限公司 | Linkage mechanism, beam limiter and X-ray machine |
| US10252968B2 (en) | 2015-07-31 | 2019-04-09 | Exxonmobil Chemical Patents Inc. | Process for making cyclohexanone |
| DE102016204870B4 (en) * | 2016-03-23 | 2023-11-23 | Siemens Healthcare Gmbh | Aperture device for collimating an X-ray beam from an X-ray device |
| CN112105919B (en) * | 2018-06-08 | 2023-08-22 | 株式会社岛津制作所 | Fluorescent X-ray analysis device and fluorescent X-ray analysis method |
Family Cites Families (10)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US2730566A (en) * | 1949-12-27 | 1956-01-10 | Bartow Beacons Inc | Method and apparatus for x-ray fluoroscopy |
| US3912936A (en) * | 1972-09-15 | 1975-10-14 | Machlett Lab Inc | X-ray image intensifier system |
| FR2391699A1 (en) * | 1976-04-09 | 1978-12-22 | Radiologie Cie Gle | RADIOGRAPHY EQUIPMENT, ESPECIALLY MAMMOGRAPHY |
| JPS536593A (en) * | 1976-07-08 | 1978-01-21 | Toshiba Corp | X-ray apparatus for diagnosis |
| DE2646638C2 (en) * | 1976-10-15 | 1986-08-14 | Siemens AG, 1000 Berlin und 8000 München | Dental X-ray diagnostic facility |
| US4096391A (en) * | 1976-10-15 | 1978-06-20 | The Board Of Trustees Of The University Of Alabama | Method and apparatus for reduction of scatter in diagnostic radiology |
| US4179100A (en) * | 1977-08-01 | 1979-12-18 | University Of Pittsburgh | Radiography apparatus |
| US4203037A (en) * | 1977-08-01 | 1980-05-13 | University Of Pittsburgh | Collimated radiation apparatus |
| JPS5685328A (en) * | 1979-12-17 | 1981-07-11 | Uni Pitsutsubaagu | Radioactive photographing apparatus |
| US4366574A (en) * | 1980-10-31 | 1982-12-28 | Technicare Corporation | Shadowgraphic slit scanner with video display |
-
1982
- 1982-01-04 US US06/337,031 patent/US4404591A/en not_active Expired - Fee Related
- 1982-12-24 CA CA000418650A patent/CA1190980A/en not_active Expired
- 1982-12-29 DE DE8282201672T patent/DE3265470D1/en not_active Expired
- 1982-12-29 EP EP82201672A patent/EP0083465B1/en not_active Expired
- 1982-12-29 JP JP57234884A patent/JPS58118733A/en active Granted
Also Published As
| Publication number | Publication date |
|---|---|
| JPH034156B2 (en) | 1991-01-22 |
| JPS58118733A (en) | 1983-07-14 |
| US4404591A (en) | 1983-09-13 |
| DE3265470D1 (en) | 1985-09-19 |
| EP0083465B1 (en) | 1985-08-14 |
| EP0083465A1 (en) | 1983-07-13 |
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