GB2176680A - Device and method for producing a visible image from non-visible radiation image - Google Patents
Device and method for producing a visible image from non-visible radiation image Download PDFInfo
- Publication number
- GB2176680A GB2176680A GB08612917A GB8612917A GB2176680A GB 2176680 A GB2176680 A GB 2176680A GB 08612917 A GB08612917 A GB 08612917A GB 8612917 A GB8612917 A GB 8612917A GB 2176680 A GB2176680 A GB 2176680A
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- GB
- United Kingdom
- Prior art keywords
- image
- visible light
- light image
- producing
- invisible radiation
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- G—PHYSICS
- G01—MEASURING; TESTING
- G01N—INVESTIGATING OR ANALYSING MATERIALS BY DETERMINING THEIR CHEMICAL OR PHYSICAL PROPERTIES
- G01N23/00—Investigating or analysing materials by the use of wave or particle radiation, e.g. X-rays or neutrons, not covered by groups G01N3/00 – G01N17/00, G01N21/00 or G01N22/00
- G01N23/02—Investigating or analysing materials by the use of wave or particle radiation, e.g. X-rays or neutrons, not covered by groups G01N3/00 – G01N17/00, G01N21/00 or G01N22/00 by transmitting the radiation through the material
- G01N23/04—Investigating or analysing materials by the use of wave or particle radiation, e.g. X-rays or neutrons, not covered by groups G01N3/00 – G01N17/00, G01N21/00 or G01N22/00 by transmitting the radiation through the material and forming images of the material
- G01N23/043—Investigating or analysing materials by the use of wave or particle radiation, e.g. X-rays or neutrons, not covered by groups G01N3/00 – G01N17/00, G01N21/00 or G01N22/00 by transmitting the radiation through the material and forming images of the material using fluoroscopic examination, with visual observation or video transmission of fluoroscopic images
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- Health & Medical Sciences (AREA)
- Engineering & Computer Science (AREA)
- Multimedia (AREA)
- Nuclear Medicine, Radiotherapy & Molecular Imaging (AREA)
- Radiology & Medical Imaging (AREA)
- Physics & Mathematics (AREA)
- Life Sciences & Earth Sciences (AREA)
- Chemical & Material Sciences (AREA)
- Analytical Chemistry (AREA)
- Biochemistry (AREA)
- General Health & Medical Sciences (AREA)
- General Physics & Mathematics (AREA)
- Immunology (AREA)
- Pathology (AREA)
- Image-Pickup Tubes, Image-Amplification Tubes, And Storage Tubes (AREA)
- Measurement Of Radiation (AREA)
- Apparatus For Radiation Diagnosis (AREA)
- Radiography Using Non-Light Waves (AREA)
Abstract
A method and system for radiation imaging includes a source (20) of invisible radiation such as an X-ray source for passing such invisible radiation through an object (12) to form an invisible radiation image of the object onto a phospher screen (24) for converting the invisible radiation image into a visible light image of the object, and a lens (26) or a tapered fibre-optic conduit (Fig. 2) for reducing the visible light image and transferring it to a microchannel plate image intensifier (50) for intensifying the reduced visible light image. The intensified reduced visible light image can be viewed directly by an observer (48) or can be projected to a camera. The image can be magnified prior to actual viewing. <IMAGE>
Description
SPECIFICATION
Device and method for producing a visible image from non-visible radiation image
The present invention relates to a device and a methodfor producing a visible image ofan object corresponding to an image of the object in invisible radiation, in particularto producing an image of an object in X-rays and gamma-rays and producing an image in visible light corresponding to the X-ray and gamma-rayimage,and more particularlyto an improved device for producing a visible, intensified image from an X-ray image.
United States Patent No.4,142,101 discloses an imaging device which produces visible light from charged or neutral particles, as well as X-rays and gamma rays, and then intensifies the visible lightto provide an image suitable for clinical observation.
The above imaging device includes a converter which is light-coupledto a visible light intensifier.
X-rays strike a phosphor screen. The resulting light is transmitted via an input fibre-optic plate to a photocathode where it produces electrons. The electrons are accelerated through a vacuum to a microchannel plate image intensifier(MCP) which multipliesthe electrons. The resulting electrons produce light by impinging upon a second phosphor screen and the light is thereafter directed via an output fibre-optic plate to a viewer.
The low intensity X-ray Image Scope ofthe above device is described further in Yin et al., "The Lixiscope" NASA Technical Memorandum 79634,
September 1978. TheTechnical Memorandum states that the "Lixiscope" is not intended to replace, or compete with, large-format medical fluoroscopic units. The "Lixiscope" is limited to small X-rayfields of about two inches due to the relatively small size limitations ofthe MCP. The "Lixiscope" is thus not practical for many clinical and industrial applications which require viewing of a relatively larger X-ray field.
There is a need therefor, for a method of X-ray imaging which offersthe image intensification advantages of the "Lixiscope" and a largerformat X-ray field.
In accordancewith afirstaspectofthepresent invention,there is provided a method for producing a visible image of an objectcorresponding to an image ofthe object in invisible radiation, comprising the steps of:
passing invisible radiation from a radiation source through an objecttoform an image of said object in invisible radiation;
producing-a visible light image of said object from said image in invisible radiation;
reducing the size of said visible light image;
intensifying said reduced visible lighe image; and
projecting said intensified reduced visible light imageforviewing.
The present invention provides a method and a system for radiation imaging. An intensified visible light image of a largerX-rayfield on an object can be produced by the present invention than has heretofore been possible.
The reducing step may include projecting the visible light image produced from a phosphor screen, or otherdeviceforproducing a visible light image corresponding to the invisible radiation image, by means of an optical lens system. The optical lens system may have one or a plurality of lenses.
Alternatively, the visible light image can be conveyed from the screen or other device to a tapered coherent fibre-optic bundle. The output end ofthe fibre-optic bundle is smallerthan its input end, which has approximately the same surface area as the converting device. The two image reducing alternatives can be combined by using the optical lens system and the tapered coherentfibre-opticbundle in tandem, in either order. In another embodiment, a system of mirror, alone or in combination with the other image reduction alternatives, may be employed to reduce the size of the visible light image.
In accordance with a second aspect ofthe present invention, there is provided a device for producing a visible image ofan object corresponding to an image of the object in invisible radiation, comprising:
a source of invisible radiation;
means for producing a visible light image corresponding to an invisible radiation image;
means for reducing the size of said visible light image; and
means for intensifying such reduced visible light image, said intensifying means including a microchannel plate amplifier.
Any suitable means of viewing the intensified reduced visible light image can be employed, such as direct viewing byan observer or indirect viewing by means of a camera. The intensified image may also be magnified priorto viewing.
By way of example only, specific embodiments of the present invention will now be described, with reference to the accompanying drawings, in which:- Fig. 1 is a schematic view of a first embodiment of device in accordance with the present invention, showing radiation emitted from a source, passing through a patient to a converting device priorto reduction by a lens before transferto an image intensifier;
Fig. 2 is a schematic view of an alternative embodiment of device, in accordance with the present invention, showing a tapered fibre-optic conduit in place of the lens of Fig. 1;
Fig. 3 is a schematicviewofa close-up ofthe imaging system of Fig. 1; and
Fig. 4is a schematic view of a close-up ofthe imaging system of Fig. 2.
Figs. 1 to 4 illustrate schematically the preferred embodiments of an imaging system 10 in which the method of the present invention is practised. The imaging system 10 is particularly well adaptedfor providing an intensified visible light image corresponding to the X-ray image or a patient, to aid in clinical diagnostics. It is also suited for providing visible imagesfrom-X-rays in a variety of other applications, including the inspection of airline luggage and the inspection of manufactured items for defects. However, the imaging system can be used with other kinds of invisible radiation in a variety of applications requiring a visible light image ofthe image produced by passing invisible radiation
through an object.
The improved imaging system may be considered
as a means for coupling the visible image correspond
ing to the relatively large field X-ray image of a
phosphor screen to the smaller input of a conventional
microchannel plate image intensifier. The present
invention provides a meansfor reducing the size of
the largefield image fortransferto the microchannel
plate image intensifier. Heretofore, the breadth ofthe
X-ray field which could be viewed using an image
intensifier system was limited to approximatelytwo
inches (50.8 mm).
The imaging system 10 includes generally, a radia
tion source, a means for producing visible radiation
from invisible radiation, a means for reducing the size
ofthe visible radiation image and an image intensifier.
Fig. 1 showsanX-raytube20,oranyothersuitable
X-ray source, and a phosphor screen or scintillator 24 for producing visible radiation from invisible radia
tion. The phosphor screen 24 is shaped to optimize the
system optics. For example, the surfaces ofthe screen can be coplanar, as shown,orcurved. The shape is dictated by the requirements of the particular system.
Apatientl2 is positioned between the X-ray tube 20 and the phosphor screen 24. The X-rays 22 emitted from source 20 pass th rough a portion ofthe patient
12 and produce an X-ray image or shadow on screen
24. The phosphorscreen 24 produces a visible image
which corresponds to the X-ray image of the patient.
The phosphor screen 24 is relatively large compared
with the phosphor screens ofthe aforementioned
Lixiscope. Thus, the image projected encompasses a
relatively larger area ofthe patients's anatomy.
Prototypes of imaging system 10 have utilized a
five-inch (127 mm) diameter screen. Larger imaging
field dimensions are expected.
imaging system 10 also includes an optical image
reducing system which may include a lens system 26 (Figs. 1 and 3), a tapered coherent fibre optic-bundle
56 (Figs. 2 and 4), a system of mirrors (notshown) or any combination ofthe three, to reduce the size ofthe
visible light image transferred to the image intensifier
50. Referring to Fig. 1, a housing 60 seals the imaging
system 10 againstthe entrance of visible light or other radiation from any source otherthan the visible light image produced by phosphor screen 24.
The image intensifier 50 can be any suitable known
visible light image intensifier, but preferably includes
an inputfibre-optic plate 30, a photocathode 32, a
microchannel plate amplifier36, a phosphor screen 40
and an output fibre-optic plate 42 at output end 44. The microchannel plate amplifier-36 is separated in space from the photocathode 32 and the phosphor screen
40, respectively, by vacuum regions 34 and 38.
The visible light passes through the inputfibre-optic plate30 tothe photocathode 32. The photocathode 32
emits electrons to produce an electron image corres pondingto the visible light image. The electrons are
accelerated through vacuum region 34 and focussed onthemicrochannel plateamplifier36wheretheyare
multiplied. The resultant intensified electron image is
then accelerated through vacuum region 38 toward
phosphor screen 40 where a corresponding intensi
fied, reduced visible light image is produced. The
intensified, reduced visible light image is directed toward output end 44 by outputfibre-optic plate 42.
Image intensifiers having microchannel plates such as the one described herein are commercially available.
The output image can be viewed directly by an observer 48 as shown in the drawings, or indirectly by means of a camera attachment (not shown). The intensified, reduced visible light image can be magnifiend priortoviewing by placing a suitable magnifying lens at output end 44
In an alternative embodiment of the imaging system 10, shown in Figs. 2 and 4, a tapered coherent fibre-optic bundle 56 having an input surface 54 and an output surface 58 provides the means for reducing the sizeofthe large field visible light image of phosphor screen 24. The surfacearea of input surface 54 is approximately equal to the surface area ofthe screen 24. The surface area of output end 58 is approximately equal to the surface area ofthe input end 28 ofthe image intensifier 50.When the tapered coherent fibre optic bundle 56 is used to reduce the visible light image, the phosphor may be coated on the inputsurface 54, ratherthan connecting a separate phosphor screen 24to thefibre-optic conduit 56.
Tapered coherentfibre-optic bundles are commerciallyavailable and have been usedforboththemagni- fication and reduction of images.
Combinations of lenses, mirrors and fibre-optic tapers may be used in orderto accomplish the image reduction through one or more stages. Although these techniques of image reduction arewell-known in the art of optical image formation, they have not heretofore been used in combination with image intensifica tion.
The choice of a specific embodimentwill be influenced by consideration such as apparatus size, image quality,the desired amount of image reduction, light collection efficiency, patient X-ray exposure and component cost and availability. Those versed in the artwill understand the inter-relationship among these factors and the consequent limitations of this method.
In general,fora given embodiment,the greaterthe amount of image reduction, the poorerwill be the light collection efficiency and the greaterwill be the X-ray exposure required to produce a given quality offinal image. In medical applications, that relationship will be the primary consideration and the limiting factor; in industrial inspection applications much larger objectfields are practical because greaterX-ray doses can be used.
The method of the present invention is practiced by utilizing the imaging system 10 described hereinabove. As shown schematically in the drawings, the method begins by passing invisible radiation, such as
X-rays 22, from an invisible radiation source, such as the X-raytube 20, through an object, such as patient 12, to form an invisible radiation image ofthe object.
The method proceeds by producing a visible light image ofthe object corresponding to the invisible radiation image. Thevisible light image is obtained by projecting the X-ray image onto a phosphor screen 24 to produce the visible light image. Thevisible light image is then reduced in size by means ofthe lens 26, thetapered fibre-opticconduit 56, or a combination of the two. The method is completed by intensifying the reduced visible light image for viewing. The lattertwo steps are achieved by utilizing the microchannel plate image intensifier 50 of imaging system 10. An additional step of magnifying the intensified reduced visible light image can be employed.
The imaging method and system ofthe present
invention improves the field of observation on a patient oran object by providing a larger field than has been heretofore provided and by combining the large field with the advantages offered by conventional image intensification devices.
Claims (29)
1. Adeviceforproducing avisibleimageofan object corresponding to an image ofthe objection invisible radiation, comprising:
a source of invisible radiation;
means for producing a visible light image corresponding to an invisible radiation image; means for reducing the size of said visible light image; and
meansforintensifying such rduced visible light image, said intensifying means including a microchannel plate amplifier.
2. A device as claimed in claim 1,wherein said source of invisible radiation is an X-ray source.
3. Adevice as claimed in claim 1 or claim 2, wherein said means for producing said visible light image is a scintillator material.
4. A device as claimed in any of claims 1 to 3, wherein said means for producing said visible light image is a phosphorscreen.
5. A device as claimed in any of claims 1 to 4, wherein said reducing means is an optical imaging system having a lens system, said means for producing said visible light image, said optical imaging system and said intensifying means being housed in a chamber sealed againstthe entrance of all light other than said visible light image.
6. A device as claimed in any of claims 1 to 5, wherein said optical imaging system comprises a tapered coherent fibre-optic bundle, said tapered coherent fibre-optic bundle having an input end and an output end, said output end having a surface area smallerthanthe surface area of said input end.
7. A device as claimed in any of claims 1 to 6, wherein said optical imaging system comprising a system of mirrors.
8. A device as claimed in any of claims 1 to 7, wherein said reducing means is a tapered coherent fibre-optic bundle having an input end and an output end, said input end having approximatelythesame area as the image forming surface of said means for producing said visible light image, and said output end having a smaller area than the area of said input end, and said means for producing said visible light image, said tapered coherentfibre-optic bundle, and said intensifying means being housed in a chamber sealed againstthe entrance of all light other than said visible light image.
9. A device as claimed in claim 8, wherein said meansforproducing said visible light image is a phosphorcoating on said input end of said tapered coherentfibre-optic bundle.
10. A device as claimed in claim 8, wherein said means for producing said visible light image is a phosphor screen coupled to said input end of said tapered coherent fibre-optic bundle.
11. A device as claimed in claim 1,wherein said intensifying means is an image intensifier having a sealed chamber, an input fibre-optic plate, a photocathode connected to said input fibre-optic plate, a microchannel plateamplifierspaced in avacuumfrom said photocathode, an output phosphor screen spaced in a vacuum from said microchannel plate amplifier, and an outputfibre- optic plate, all being housed within said sealed chamber.
12. A device as claimed in any of claims 1 toll, further comprising a video camera for receiving and projecting said intensified reduced visible light image.
13. Advice as claimed in any of claims 1 to 12, furthercomprising meansformagnifying said intensified reduced visible light imageforviewing.
14. A device as claimed in any of claims 1 to 13, wherein said reducing means is a system of mirrors.
15. Adeviceasclaimedinanyofclaimsl to 14, wherein said reducing means further comprises a tapered coherent fibre-optic bundle in combination with said system of mirrors.
16. A method for producing a visible image of an objectcorresponding to an image ofthe object in invisible radiation, comprising the steps of:
passing invisible radiation from a radiation source through an object to form an image of said object in invisible radiation;
producing a visible light image of said object from said image in invisible radiation;
reducing the size of said visible light image;
intensifying said reduced visible light image; and
projecting said intensified reduced visible light imageforviewing.
17. A method as claimed in claim 16, wherein said step of producing said visible light imagefrom said invisible radiation image comprises projecting said invisible radiation image onto a phosphor screen.
18. A method as claimed in claim 16 orclaim 17, wherein said step of reducing the size of said visible light image comprises conveying said visible light image from means for producing visible light from invisible radiation, by means of an optical image reducing system.
19. A method as claimed in claim 18, wherein said optical image reducing system includes a lens system.
20. A method as claimed in claim 18 or 19, wherein said optical image reducing system includes a tapered coherent fibre-optic bundle.
21. A method as claimed in anyofclaims 18to 20, wherein said optical image reducing system includes a system of mirrors.
22. A method as claimed in any of claims 16 to 21, wherein said step of intensifying said reduced visible light image comprises transferring said reduced visible light image to a visible light image intensifier.
23. .A method as claimed in claim 22, wherein said image intensifier includes an inputfibre-optics plate for conveying said reduced visible light image, a photocathodeforproducing an electron imagefrom said reduced visible light image, a microchannel plate amplifier, spaced from said photocathode in a vacuum chamber, for multiplying the electrons forming said electron image, an output phosphor screen spaced from said microchannel plate amplifier in said vacuum chamberfor producing an intensified, reduced visible lightimage,from said amplified electron image, said intensified, reduced visible lightimagecorresponding to said invisible radiation image of said object, and an output fibre-optics plate for conveying said intensified reduced visible-light image to a viewer.
24. A method as claimed in anyofclaims 16to 23, wherein said projecting step comprises displaying said intensified reduced visible light image for direct viewing by an observer.
25. A method as claimed ih any of claims 1 6to 24, further co mprisin g th e step of magnifying said intensified reduced visible light image before displaying itforsaid observer.
26. A method as claimed in any of claims 1 6to 25, wherein said projecting step comprises projecting said intensified reduced visible lightimageto a camera.
27. A method as claimed in any of claims 16to 26, wherein said radiation source is an X-ray source.
28. A method for producing a visible image of an objectto an image ofthe object in invisible radiation, substantially as herein described, with reference to, and as illustrated in the accompanying drawings.
29. A device for producing a visible image of an object corresponding to an image ofthe object in invisible radiation, substantially as herein described, with reference to and as illustrated in the accompanying drawings.
Applications Claiming Priority (1)
| Application Number | Priority Date | Filing Date | Title |
|---|---|---|---|
| US73861685A | 1985-05-28 | 1985-05-28 |
Publications (2)
| Publication Number | Publication Date |
|---|---|
| GB8612917D0 GB8612917D0 (en) | 1986-07-02 |
| GB2176680A true GB2176680A (en) | 1986-12-31 |
Family
ID=24968754
Family Applications (1)
| Application Number | Title | Priority Date | Filing Date |
|---|---|---|---|
| GB08612917A Withdrawn GB2176680A (en) | 1985-05-28 | 1986-05-28 | Device and method for producing a visible image from non-visible radiation image |
Country Status (4)
| Country | Link |
|---|---|
| JP (1) | JPS6231928A (en) |
| DE (1) | DE3617315A1 (en) |
| GB (1) | GB2176680A (en) |
| NL (1) | NL8601332A (en) |
Cited By (3)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| EP0291299A1 (en) * | 1987-05-11 | 1988-11-17 | General Electric Company | Digital radiographic imaging system and method therefor |
| US4933961A (en) * | 1987-04-10 | 1990-06-12 | British Aerospace Public Limited Company | Imaging system |
| EP0597725A1 (en) * | 1992-11-13 | 1994-05-18 | Debex (Proprietary) Limited | System for scanning bodies |
Citations (6)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| GB1488829A (en) * | 1973-10-11 | 1977-10-12 | Optische Ind De Oude Delft Nv | Method and apparatus for x-ray examination |
| US4203037A (en) * | 1977-08-01 | 1980-05-13 | University Of Pittsburgh | Collimated radiation apparatus |
| US4210812A (en) * | 1977-06-02 | 1980-07-01 | The Foundation: The Assn. of Japan General Denistry | X-Ray imaging diagnostic apparatus with low X-ray radiation |
| US4300046A (en) * | 1978-07-12 | 1981-11-10 | Diagnostic Information, Inc. | Panel type X-ray image intensifier tube and radiographic camera system |
| GB2133656A (en) * | 1983-01-13 | 1984-07-25 | John K Grady | Multiple x-ray image scanners |
| GB2165730A (en) * | 1984-10-15 | 1986-04-16 | John K Grady | X-ray system |
-
1986
- 1986-05-23 DE DE19863617315 patent/DE3617315A1/en not_active Withdrawn
- 1986-05-26 NL NL8601332A patent/NL8601332A/en not_active Application Discontinuation
- 1986-05-28 GB GB08612917A patent/GB2176680A/en not_active Withdrawn
- 1986-05-28 JP JP61123212A patent/JPS6231928A/en active Pending
Patent Citations (6)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| GB1488829A (en) * | 1973-10-11 | 1977-10-12 | Optische Ind De Oude Delft Nv | Method and apparatus for x-ray examination |
| US4210812A (en) * | 1977-06-02 | 1980-07-01 | The Foundation: The Assn. of Japan General Denistry | X-Ray imaging diagnostic apparatus with low X-ray radiation |
| US4203037A (en) * | 1977-08-01 | 1980-05-13 | University Of Pittsburgh | Collimated radiation apparatus |
| US4300046A (en) * | 1978-07-12 | 1981-11-10 | Diagnostic Information, Inc. | Panel type X-ray image intensifier tube and radiographic camera system |
| GB2133656A (en) * | 1983-01-13 | 1984-07-25 | John K Grady | Multiple x-ray image scanners |
| GB2165730A (en) * | 1984-10-15 | 1986-04-16 | John K Grady | X-ray system |
Cited By (5)
| Publication number | Priority date | Publication date | Assignee | Title |
|---|---|---|---|---|
| US4933961A (en) * | 1987-04-10 | 1990-06-12 | British Aerospace Public Limited Company | Imaging system |
| EP0291299A1 (en) * | 1987-05-11 | 1988-11-17 | General Electric Company | Digital radiographic imaging system and method therefor |
| EP0597725A1 (en) * | 1992-11-13 | 1994-05-18 | Debex (Proprietary) Limited | System for scanning bodies |
| US5404387A (en) * | 1992-11-13 | 1995-04-04 | Hammond; David J. | Body scanning system |
| AU666587B2 (en) * | 1992-11-13 | 1996-02-15 | Debex (Proprietary) Limited | Body scanning system |
Also Published As
| Publication number | Publication date |
|---|---|
| NL8601332A (en) | 1986-12-16 |
| DE3617315A1 (en) | 1986-12-04 |
| JPS6231928A (en) | 1987-02-10 |
| GB8612917D0 (en) | 1986-07-02 |
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Legal Events
| Date | Code | Title | Description |
|---|---|---|---|
| WAP | Application withdrawn, taken to be withdrawn or refused ** after publication under section 16(1) |