GB1147384A – Radiation camera
– Google Patents
GB1147384A – Radiation camera
– Google Patents
Radiation camera
Info
Publication number
GB1147384A
GB1147384A
GB92967A
GB92967A
GB1147384A
GB 1147384 A
GB1147384 A
GB 1147384A
GB 92967 A
GB92967 A
GB 92967A
GB 92967 A
GB92967 A
GB 92967A
GB 1147384 A
GB1147384 A
GB 1147384A
Authority
GB
United Kingdom
Prior art keywords
pulses
image
detector
electrons
gamma
Prior art date
1967-01-06
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
Application number
GB92967A
Inventor
Peter James Harvey
Current Assignee (The listed assignees may be inaccurate. Google has not performed a legal analysis and makes no representation or warranty as to the accuracy of the list.)
Ekco Electronics Ltd
Original Assignee
Ekco Electronics Ltd
Priority date (The priority date 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 date listed.)
1967-01-06
Filing date
1967-01-06
Publication date
1969-04-02
1967-01-06
Application filed by Ekco Electronics Ltd
filed
Critical
Ekco Electronics Ltd
1967-01-06
Priority to GB92967A
priority
Critical
patent/GB1147384A/en
1968-01-04
Priority to FR1554015D
priority
patent/FR1554015A/fr
1969-04-02
Publication of GB1147384A
publication
Critical
patent/GB1147384A/en
Status
Expired
legal-status
Critical
Current
Links
Espacenet
Global Dossier
Discuss
Classifications
G—PHYSICS
G21—NUCLEAR PHYSICS; NUCLEAR ENGINEERING
G21G—CONVERSION OF CHEMICAL ELEMENTS; RADIOACTIVE SOURCES
G21G4/00—Radioactive sources
G21G4/04—Radioactive sources other than neutron sources
G21G4/06—Radioactive sources other than neutron sources characterised by constructional features
G21G4/08—Radioactive sources other than neutron sources characterised by constructional features specially adapted for medical application
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
G01T1/161—Applications in the field of nuclear medicine, e.g. in vivo counting
G01T1/164—Scintigraphy
G01T1/1641—Static instruments for imaging the distribution of radioactivity in one or two dimensions using one or several scintillating elements; Radio-isotope cameras
G01T1/1645—Static instruments for imaging the distribution of radioactivity in one or two dimensions using one or several scintillating elements; Radio-isotope cameras using electron optical imaging means, e.g. image intensifier tubes, coordinate photomultiplier tubes, image converter
Abstract
1,147,384. Television. EKCO ELEGTRONICS Ltd. 5 Jan., 1968 [6 Jan., 1967], No. 929/67. Heading H4F. In a radiation camera, gamma photon emissions from an object O, Fig. 1, pass via a multihole collimator 1 to a crystal detector matrix 2 which converts the emissions into optical signal pulses, i.e. converts the gamma image into a light image. These optical signal pulses are fed with demagnification by optical fibres 3 to a photo-cathode 4 of a 2-stage image intensifier 5 of the phosphor/photo-cathode sandwich type. The amplified optical signal pulses from phosphor 6 are fed by lens or fibre optics to an optical gate 12 which is responsive to a sensing signal derived from the output phosphor 6 of the image intensifier across resistive load 7. Electrical sensing signal pulses are developed across this load proportional to the optical signal pulses released from the detector which correspond to the energy of the incident gamma photons. Each sensing signal pulse is processed in a pulse amplifier 8 and a pulse height analyser 9. Pulses in a predetermined amplitude range corresponding to the wanted gamma energy range are accepted by the analyser to give rise to standard output pulses which are amplified 10 and used to switch the optical gate. This gating operation also rejects scattered and background radiation and limits the noise from the image intensifier. The light output from the optical gate 12 is coupled by lens 17 or fibre optics to the input photo-cathode 19 of storage tube 18, the sequential pulses of electrons from which are accelerated by electrode 20 on to target 22 where proportional positive electrical charges are set up by secondary emission, the excess electrons being collected by the collector grid 21. The storage tube integrates the sequential optical signal pulses to form an electrical charge image on the target of the original radioisotope distribution in the body O. Read-out of the charge image is by means of raster scanning by beam 24 and the output is fed to a conventional CRT, the presentation being in monochrome or colour, various colours being used to display various levels of signal intensity. The storage tube 18 operates on the principle of the image orthicon but with relatively non-destructive read-out. The storage target 22 is a mesh with an insulating coating on the photo-cathode side which releases secondary electrons in excess of the electrons incident from the photocathode thus setting up a positive charge on the insulator. The secondary electrons are collected by the collector grid or mesh 21 which is held positive. Beam 24 of electrons scan the target at a slow rate (1 frame/sec.) and the electrons are de-accelerated to near zero velocity by electrode 23 and then modulated by the positive charge pattern on the target, some of the reading beam passing through the target to the collector 21, the remainder being reflected and amplified by multiplier 25 to form the output signal. For operation with positron-emitting isotopes, gating is on the basis of coincident detection of the annihilation gamma photons. The multi-hole collimator is removed and the gamma image is formed by detecting one of the annihilation gamma photons in the crystal matrix 2 as before, and the second in a scintillation counter 43. The pulses of amplitude proportional to the incident gamma energy are produced by this counter, amplified 44 and analysed 45 and the outputs of the analysers 45 and 9 are fed to a coincidence circuit 15 (switch 16 being in the other position). Gate 12 is thus opened by the coincident detection of the two gamma photons. In a second embodiment, Fig. 4, a singlestage image intensifier 5 is optically coupled directly to a crystal detector 2 or a detector matrix. When the detector 2 is a single crystal detector the light image is formed at the output of the detector by a fibre optic face-plate 3a which is integral to the construction of both detector and intensifier. The intensified light pulses from output phosphor 6 are coupled by lens 11 to an intensifier gate 12a which is a 2-stage device comprising a first photo-cathode/ phosphor gap intensifying stage and a second photo/phosphor gap gating stage switched by the gating pulse amplifier 10 as in Fig. 1.
GB92967A
1967-01-06
1967-01-06
Radiation camera
Expired
GB1147384A
(en)
Priority Applications (2)
Application Number
Priority Date
Filing Date
Title
GB92967A
GB1147384A
(en)
1967-01-06
1967-01-06
Radiation camera
FR1554015D
FR1554015A
(en)
1967-01-06
1968-01-04
Applications Claiming Priority (1)
Application Number
Priority Date
Filing Date
Title
GB92967A
GB1147384A
(en)
1967-01-06
1967-01-06
Radiation camera
Publications (1)
Publication Number
Publication Date
GB1147384A
true
GB1147384A
(en)
1969-04-02
Family
ID=9713002
Family Applications (1)
Application Number
Title
Priority Date
Filing Date
GB92967A
Expired
GB1147384A
(en)
1967-01-06
1967-01-06
Radiation camera
Country Status (2)
Country
Link
FR
(1)
FR1554015A
(en)
GB
(1)
GB1147384A
(en)
Cited By (1)
* Cited by examiner, † Cited by third party
Publication number
Priority date
Publication date
Assignee
Title
US4255666A
(en)
*
1979-03-07
1981-03-10
Diagnostic Information, Inc.
Two stage, panel type x-ray image intensifier tube
1967
1967-01-06
GB
GB92967A
patent/GB1147384A/en
not_active
Expired
1968
1968-01-04
FR
FR1554015D
patent/FR1554015A/fr
not_active
Expired
Cited By (1)
* Cited by examiner, † Cited by third party
Publication number
Priority date
Publication date
Assignee
Title
US4255666A
(en)
*
1979-03-07
1981-03-10
Diagnostic Information, Inc.
Two stage, panel type x-ray image intensifier tube
Also Published As
Publication number
Publication date
FR1554015A
(en)
1969-01-17
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