EP0064913B1 - Multidétecteur de rayons X - Google Patents

Multidétecteur de rayons X Download PDF

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Publication number
EP0064913B1
EP0064913B1 EP82400769A EP82400769A EP0064913B1 EP 0064913 B1 EP0064913 B1 EP 0064913B1 EP 82400769 A EP82400769 A EP 82400769A EP 82400769 A EP82400769 A EP 82400769A EP 0064913 B1 EP0064913 B1 EP 0064913B1
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EP
European Patent Office
Prior art keywords
electrodes
multidetector
chamber
main
rays
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
Application number
EP82400769A
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German (de)
English (en)
French (fr)
Other versions
EP0064913A3 (en
EP0064913A2 (fr
Inventor
Robert Allemand
Jean-Jacques Gagelin
Edmond Tournier
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.)
Commissariat a lEnergie Atomique et aux Energies Alternatives CEA
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Commissariat a lEnergie Atomique CEA
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Publication of EP0064913A2 publication Critical patent/EP0064913A2/fr
Publication of EP0064913A3 publication Critical patent/EP0064913A3/fr
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Publication of EP0064913B1 publication Critical patent/EP0064913B1/fr
Expired legal-status Critical Current

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    • H—ELECTRICITY
    • H01—ELECTRIC ELEMENTS
    • H01J—ELECTRIC DISCHARGE TUBES OR DISCHARGE LAMPS
    • H01J47/00—Tubes for determining the presence, intensity, density or energy of radiation or particles
    • H01J47/02—Ionisation chambers

Definitions

  • the present invention relates to a method for manufacturing an X-ray multidetector, and in particular X-rays which have passed through an object or an organ after having been emitted by a source emitting towards the object or the organ, these X-rays in the form of a planar beam having a wide angular opening and a small thickness.
  • This invention applies more particularly to the manufacture of multidetectors intended for tomography or radiography of organs, but also to industrial control, such as baggage control for example.
  • the X-ray multidetectors make it possible to measure the absorption of an X-ray beam passing through an object or an organ, this absorption being linked to the density of the tissues of the organ examined or to the density of the materials constituting the object studied.
  • a first type of ionization X-ray multidetector used in radiography and tomography is multicellular and comprises cells delimited by conductive plates perpendicular to the plane of the X-ray beam and brought alternately to positive and negative potentials. These cells are located in a sealed enclosure containing an ionizable gas.
  • the advantages of this type of multidetector are as follows: it provides good collimation of X-rays when the plates used in the detection cells are made of a very absorbent material; the collection time of the charges resulting from the ionization of the gas by X-rays is very short because of the small spacing of the conductive plates and the good separation between the detection cells.
  • this type of multidetector has significant drawbacks: it is very difficult to manufacture and therefore expensive. In addition, if it is desired to reduce the thickness of the plates in order to increase the quantity of X-rays detected, there is a reduction in collimation due to the small thickness of the plates; this small thickness of the plates also causes a very large microphone. Finally, multidetectors of this type, as indicated above, have a great complexity of production which results in a high manufacturing cost; they require mounting in a dusted room, because any dust on one of the plates can cause ignition or deterioration of the leakage current between two consecutive plates. It is added to these drawbacks that the numerous electrodes used require very numerous electrical connections, inside the sealed chamber, which poses difficult problems of reliability of the welds of the connections on the electrodes.
  • a second type of multidetector which has a much simpler structure, but which is not perfect.
  • This other type of multidetector includes a sealed chamber containing a gas ionizable by rays from the organ or object and, in this chamber, a plate for collecting the electrons resulting from the ionization of the gas; this plate is parallel to the plane of the beam of incident rays and it is brought to a positive high voltage.
  • a series of electrodes for collecting the ions resulting from the ionization of the gas by the X-rays coming from the object is arranged in parallel and facing the preceding plate; these ion collection electrodes are brought to a potential close to zero and are directed towards the source which emits the X-rays, in the direction of the object. They are located in a plane parallel to the plane of the beam of the incident rays and respectively provide a measurement current as a function of the quantity of ions obtained by the ionization of the gas opposite each electrode, under the effect of the rays coming from the object or organ, in a direction corresponding to that of the incident rays.
  • This type of multidetector has certain advantages: there are no longer, as in the previously mentioned multidetector, separation plates; this eliminates any annoying phenomenon of microphony. Due to the removal of these separation plates, the quantity of X-rays detected is maximum; the realization of this type of multidetector is simpler and it is very little sensitive to dust. Finally, it is possible, without connection inside the sealed chamber, to collect, inside the chamber, the signals available on each of the electrodes brought to a potential close to zero.
  • the object of the present invention is to remedy this drawback and in particular to manufacture a multidetector of this second type, in a simple and inexpensive manner, without welding on the electrodes inside the enclosure for connecting these, by connections, at points outside the enclosure.
  • the subject of the invention is an X-ray multidetector capable of detecting a thin plane X-ray beam, this multidetector comprising a sealed enclosure filled with an ionizable gas and, in this enclosure, at least one main multidetector assembly comprising a flat conductive plate, electrically isolated from the enclosure, parallel to the X-ray beam and brought to a first potential, and a plurality of planar electrodes parallel to the plate, isolated from this plate, these electrodes being isolated from each other, brought to a second potential and extending in the direction of the rays supplied by the source, this multidetector further comprising at least one other auxiliary multidetector assembly, of structure identical to that of the main multidetector assembly, the plate of this auxiliary multidetector being worn at a third potential and the electrodes being brought to the second potential, characterized in that the electrodes of a main multidetector cipal as well as main connections between these electrodes and measurement points outside the enclosure making it possible to
  • the electrodes and the connections consist of conductive deposits on the insulating plate.
  • these conductive deposits are etched metallized deposits.
  • the conductive deposits are metallized deposits etched on the insulating plate.
  • the multidetector comprises, for each conductive plate, an electrically isolated connection from the enclosure and passing through it in leaktight manner, which makes it possible to connect said conductive plate to a high voltage source external to the enclosure.
  • the multidetector comprises a plurality of main and auxiliary multidetector assemblies.
  • FIG. 1 shows schematically and in perspective, a multidetector that it is possible to manufacture in accordance with the invention.
  • This multidetector comprises a plate 1 brought to a first potential (high positive voltage + HT) and, opposite, a series of electrodes 2 brought to a second potential (close to zero volts).
  • This plate and these electrodes are located in a sealed main chamber 3, shown diagrammatically and which contains at least one ionizable gas, such as xenon for example.
  • This multidetector makes it possible to detect the X-rays which have passed through an object or an organ 0, these rays being supplied by a point or linear source S which emits in the direction of the object or the organ, a plane beam F of X-rays incidents.
  • This beam has a wide angular opening and a small thickness.
  • the plate 1 is parallel to the plane of the beam of incident rays, while the plane electrodes 2 are located in a plane parallel to the plane of the beam of incident rays, opposite the plate 1.
  • the plate 1 which is brought to a positive potential neighboring a few kilovolts, is an electron collection plate, while the electrodes 2 are ion collection electrodes. These electrodes are generally carried by an insulating plate (not shown in this figure) and are electrically isolated from each other.
  • the pressure of the xenon inside the sealed chamber has a value which is a function of the energy of the X-ray to be detected (from 1 to 40 bars approximately); this gas can also be added to other gases intended to improve detection.
  • the electrodes 2 form converging bands in the direction of the source S.
  • FIG. 2 schematically represents a front view of the preceding multidetector.
  • This figure shows the plate 1 brought to a positive potential + HT as well as the electrodes 2 brought to a potential close to zero volts; these electrodes are supported by an electrically insulating plate 4 and each of them is connected to an amplifier 5 which makes it possible to draw the current flowing in each of the electrodes; these currents are applied to a processing (not shown) and visualization system, which makes it possible to visualize the body or object 0 traversed by the X-rays emitted by the source S.
  • a processing not shown
  • visualization system which makes it possible to visualize the body or object 0 traversed by the X-rays emitted by the source S.
  • vertical dotted lines the field lines.
  • Xe + represents the positive xenon ions which go towards the electrodes 2 and by e- the electrons which go towards the plate 1; these ions and these electrons resulting from the ionization of xenon by X-rays from the object or organ 0.
  • the electrons are replaced by the negative ions, formed from additional gas.
  • the electrodes 2 and the main connections between these electrodes and points outside the enclosure, making it possible to take the currents flowing respectively in these electrodes, are produced on a main face of an electrically insulating plate 4. These connections are shown more fully in Figures 5 and 6. These main connections are electrically isolated from the enclosure and pass through them in leaktight manner, opposite the source.
  • FIG. 3 shows schematically and in perspective, another multidetector that it is also possible to manufacture in accordance with the invention.
  • This multidetector comprises a sealed chamber 6, metallic for example, containing at least one ionizable gas such as xenon for example this chamber is subdivided into two ionization chambers: a main ionization chamber 3 and an auxiliary ionization chamber 7
  • the main ionization chamber 3 contains, like the multidetector of FIG. 1, a plate 1 brought to a first potential (high positive voltage + HT) and a series of electrodes 2 brought to a second potential (close to zero volts). ).
  • the plate 1 and the electrodes 2 in the main ionization chamber 3 form a main multidetector assembly.
  • these electrodes are planar and are carried by an electrically insulating plate 4; the plate 1 and the electrodes 2 are located in a plane parallel to the plane of the X-ray beam from the source S (this beam being incompletely shown in the figure).
  • the electrodes 2 converge in the direction of the source S.
  • Each of the electrodes 2 of the main ionization chamber 3 is connected to an amplifier 5 which makes it possible to take, for processing, the current flowing in each of these electrodes.
  • the auxiliary ionization chamber 7 is attached to the main chamber to compensate for the diffusion current coming from the X-rays scattered by the member 0.
  • the auxiliary ionization chamber 7 contains, like the main ionization chamber, a plate 10 parallel to the plane of the incident X-ray beam is brought to a third potential (high negative voltage - HT), as well as a series of 11 flat electrodes, parallel to the plane of the incident X-ray beam, and located on another face of the insulating plate 4 which carries the electrodes 2 of the main ionization chamber 3.
  • the plate 10 and the electrodes 11 in the auxiliary chamber 7 form an auxiliary multidetector assembly.
  • the electrodes 11 are brought, like the electrodes 2 of the main ionization chamber, to a potential close to zero. They are respectively connected by connections 12, to the corresponding electrodes of the main ionization chamber 3.
  • the electrodes 11 of the auxiliary ionization chamber and the electrodes 2 of the main ionization chamber are preferably identical and located next to each other.
  • the auxiliary ionization chamber 7 makes it possible, as will be seen in detail below, to compensate, for the subsequent treatment of the currents originating from the amplifiers 5, the diffused currents which circulate in each electrode of the main ionization chamber and which originate X-rays scattered by the object or organ 0.
  • the electrodes 11 of the auxiliary ionization chamber 7 are electrodes for collecting electrons e- or negative ions, while the plate 10 is a plate for collecting the Xe + ions coming from the ionization of the xenon contained in the auxiliary chamber 7, by the X-rays scattered by the object or the organ 0.
  • the electrodes of the auxiliary ionization chamber are located opposite the electrodes of the main ionization chamber and the high positive and negative voltages have the same absolute value.
  • Reference 50 designates a diaphragm.
  • Figure 4 schematically shows a side view of the previous multidetector.
  • a distinction is made between the source S, the object or the organ 0, one of the rays 9 emitted by the source S and, at the output of the object 0, the direct ray 13 coming from the object 0 , in the same direction as the incident ray 9; one also distinguishes in this figure one of the scattered rays 8, coming from the object 0, in a direction different from the direction of the incident ray 9.
  • one shows one of the electrodes 2 of the chamber d main ionization which is connected to an amplifier 5 and which is brought to a potential close to 0, and one of the electrodes 11 of the auxiliary ionization chamber 7, which is located opposite the electrode 2 and which is separated from this electrode by the insulating plate 4.
  • the connection 12 between the electrodes of the main and auxiliary ionization chambers has also been shown.
  • the plates 1 and 10 of the main and auxiliary ionization chambers brought respectively to potentials. positive and negative + HT and - HT.
  • the sealed chamber 6 which contains the ionizable gas has not been shown in detail; the insulating plates 42, 14 support the conductive plates 1, 10 of the main and auxiliary ionization chambers.
  • the ionizable gas is xenon
  • This ionization is represented schematically in the figure by Xe + ions which are attracted by the electrodes 2, and by electrons e- or negative ions which are attracted by the positive plate 1.
  • An ionization thus occurs opposite each of the electrodes from the main ionization chamber using X-rays from the object, in the direction of the incident rays.
  • These ion movements produce respectively in each electrode, a current 1 which is the sum of a current i n resulting from the ionization of the gas opposite each of the electrodes, under the effect of X-rays from the object. (rays represented at 13 in the figure), in a direction corresponding to that of the incident rays, and of a diffusion current t o , which results from the ionization of the gas, opposite each of the electrodes, from the rays scattered by the object, in directions which do not correspond to those of the incident X-rays.
  • the ionization chamber 7 makes it possible to compensate for this diffusion current, thanks to the ionization produced in this chamber by the scattered X-rays 8; this ionization causes the circulation, in the electrodes 11 of the auxiliary chamber, of a current I D which is cut off, thanks to the connection 12, from the parasitic diffusion current taken into account by the electrodes of the main ionization chamber .
  • the amplifiers 5 connected to each of the electrodes of the main and auxiliary ionization chambers receive a current l M which is effectively the measurement current corresponding to the ionization of the gas, caused opposite each of the electrodes of the chamber d main ionization, by the rays 13 coming from the object or the organ, in the directions which correspond to those of the incident rays 9.
  • the electrodes 2 and the main connections 15 between these electrodes and the measurement points 19 outside the enclosure are as for the multidetector of FIG. 3, produced on a main face 16 of the electrically insulating plate 4 ; these measurement points make it possible to take the currents flowing respectively in these electrodes; the main connections 15 - are electrically isolated from the enclosure and pass through them in leaktight manner, opposite the source.
  • the auxiliary multidetector assembly has a structure identical to that of the main multidetector assembly; the plate 10 of this auxiliary multidetector is brought, as indicated above, to a high negative potential and the electrodes 11 are brought to a potential close to zero.
  • the electrodes 11 of this auxiliary multidetector, as well as respective connections 17 between these electrodes 11 and secondary points 20, external to the enclosure, are produced on the other face 18 of the electrically insulating plate 4; this face 18 is opposite to the main face 16; the secondary connections 17 are electrically isolated from the enclosure and pass through them in leaktight manner, opposite the source S; the method then consists in connecting the measurement points 19 and the secondary points 20 respectively.
  • the electrodes and connections are made in the form of conductive deposits on the insulating plate; preferably, these conductive deposits are metallized deposits etched on the insulating plate.
  • the conductive plates 1 and 7 are brought respectively to a high positive potential + HT and to the potential - HT, by making a connection between each of these plates and a high voltage source external to the pregnant; this connection is electrically isolated from the enclosure and crosses it in a sealed manner.
  • Figure 5 is a schematic side sectional view of a multicut multidetector, the operation of which is comparable to that of the multidetector of Figure 3; this multidetector is manufactured, in accordance with the invention, by stacking a plurality of main and auxiliary multidetector assemblies as described in FIG. 3.
  • the multidetector of FIG. 5 is a stack of main and auxiliary multidetectors, as described in FIG. 3.
  • This stack comprises a first main multidetector assembly comprising a flat conductive plate 1 intended to be brought to a high positive voltage + HT, electrically isolated from the enclosure, (the latter being able to be constituted for example by epoxy resin).
  • This flat conductive plate is parallel to the beam F of X-rays from the object or the organ to be analyzed (not shown in this figure).
  • This first multidetector assembly also includes a plurality of planar electrodes 2 parallel to the plate 1 and extending in the direction of the X-rays of the beam F.
  • Electrodes are isolated from one another as will be seen below in detail, and are protected at a potential close to zero.
  • These electrodes as well as main connections 15 between these electrodes and measurement points 19 outside the enclosure making it possible to take the currents flowing respectively in these electrodes, are formed on one face 16 of the electrically insulating plate 4.
  • These main connections 15 are electrically isolated from the enclosure and pass through the latter in leaktight manner, opposite the source which emits the beam X of X-rays.
  • the enclosure containing an ionizable gas is constituted by the spacer insulator 21, of epoxy resin for example, the hollow interior of which forms a chamber; this spacer makes it possible to separate the electrodes 2 and the plate 1 and the chamber can contain xenon for example.
  • the covers 33 and 34 are provided in aluminum alloy, but the plates 10 and 31 are identical to the plate 10 of Figure 4.
  • the covers 33, 34 could optionally bear in a sealed manner on the plate 1 and on the insulating plate 4, to form with the electrodes 2, an elementary multidetector whose front face would be provided with a sealed window 38 .
  • At least one auxiliary multidetector assembly is produced, with a structure identical to that of the main multidetector assembly which has just been described.
  • the plate 10 of this secondary multidetector is brought to a negative high voltage - HT, while the electrodes 11 of this multidetector, whose structure is identical to that of the electrodes 2 of the main multidetector, are brought to a potential close to 0.
  • the electrodes 11 as well as the respective connections 17 between these electrodes and secondary points external to the enclosure formed by the spacers 21, 22, are formed on the other face 18 of the electrically insulating plate 4.
  • the secondary connections 17 are electrically insulated of the enclosure, the latter consisting of epoxy resin for example; these connections pass through the enclosure formed by the spacers 21, 22 in leaktight manner, opposite the source emitting the beam F ′ of X-rays.
  • the method then consists in connecting the main 15 and secondary 17 connections to the measurement points 19, for each of the electrodes, by a connector 40, shown diagrammatically in the figure. If the hollow spacers 21, 22 are closed by covers 33, 34 pressing in leaktight manner on the plates 1 and 10, a multidetector with a structure comparable to that of FIG. 3 is obtained; this multidetector making it possible to compensate, thanks to the auxiliary assembly, as mentioned above, the diffusion current present in the current taken from each of the electrodes.
  • This other stack comprises a second main multidetector formed by the plate 1 brought to the high positive voltage and electrodes 23 of ion collections, brought to a potential close to zero, connected to measurement points 24, by main connections 25; the electrodes 23 and the main connections 25 are made, as before, on a face 26 of an electrically insulating plate 27.
  • the electrodes 23 and the plate 1 are separated by a hollow insulating spacer 28.
  • a second auxiliary multidetector is formed on the other side of the insulating plate 27.
  • This auxiliary multidetector comprises electrodes 29 brought to a potential close to zero. These electrodes are isolated from each other and directed in the direction of the rays of the beam F '. They are connected respectively by secondary connections 30, to external points.
  • This auxiliary multidetector assembly also comprises a plate 31 brought to a negative high voltage - HT and separated from the electrodes 29 by an insulating spacer 32; the various spacers, electrodes and plates of this stack are made integral by covers 33, 34 and fixing means 35; the covers, the spacers, the plates and connections, as well as the plates supporting the electrodes, are made integral so that the assembly forms a sealed hollow volume 36, containing xenon for example.
  • the different chambers formed in this hollow volume can be brought into communication by openings such as 37 made in the plates supporting the electrodes and in the plate 1 brought to high positive voltage + HT.
  • the electrodes 29 and the plate 31 of the auxiliary chamber of the second stack form a compensation chamber for the diffusion currents which disturb the currents measured on the electrodes 23 of the main chamber of this second stack.
  • the connector 41 allows the electrodes 23 and 29 of this second stack to be connected respectively to the measurement points 24.
  • a waterproof window 38 maintained by a flange 39, is arranged on the front face of the multidetector.
  • the detector shown in this figure comprises two stacks which make it possible to make two parallel sections of an organ or an object to be analyzed; this multidetector could comprise a single stack or more than two stacks. It is also obvious that each multidetector may not include the compensation chamber for diffusion currents; the invention relates in fact to the production of the electrodes and their connections with external points, these electrodes and these connections being produced in the form of conductive deposits on an insulating plate. These deposits are metallized and engraved on the insulating plate.
  • the invention also relates, and above all, to the manufacture of a multidetector by stacking such insulating plates equipped with conductive deposits and insulating spacers, this stack producing the insulating enclosure filled with detector gas.
  • Figure 6 is a top view of the detector of Figure 5, according to a section taken at the plate 4 for example.
  • the electrodes 2 directed in the direction of the rays of the X-ray beam F and the main connections 15 between these electrodes and measurement points 19 external to the multidetector. It is also better to distinguish that the electrodes 2 and the connections 15 are produced in the form of conductive deposits on the insulating plate 4. It is quite obvious that the electrodes 11, 23 and 29 are produced in the same way.
  • the plates and electrodes of the main and secondary ionization chambers of each stack are preferably produced in the form of a copper deposit on an insulating support.
  • the number of cells in each chamber can be greater than 500, for an opening angle of the X-ray beam greater than 40 °; in this case, the step between each of the electrodes of each chamber is approximately 1 mm.
  • the insulating plate which supports the electrodes of the main and secondary chambers is located midway between the plates which are respectively brought to positive and negative potential. The distance between these plates is approximately 14 mm and the ion collection time is close to 10 ms.

Landscapes

  • Measurement Of Radiation (AREA)
  • Apparatus For Radiation Diagnosis (AREA)
  • Electron Tubes For Measurement (AREA)
  • Analysing Materials By The Use Of Radiation (AREA)
EP82400769A 1981-05-06 1982-04-28 Multidétecteur de rayons X Expired EP0064913B1 (fr)

Applications Claiming Priority (2)

Application Number Priority Date Filing Date Title
FR8109000 1981-05-06
FR8109000A FR2505492B1 (sv) 1981-05-06 1981-05-06

Publications (3)

Publication Number Publication Date
EP0064913A2 EP0064913A2 (fr) 1982-11-17
EP0064913A3 EP0064913A3 (en) 1983-08-03
EP0064913B1 true EP0064913B1 (fr) 1986-04-02

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EP82400769A Expired EP0064913B1 (fr) 1981-05-06 1982-04-28 Multidétecteur de rayons X

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US (1) US4481420A (sv)
EP (1) EP0064913B1 (sv)
JP (1) JPS57187679A (sv)
DE (1) DE3270211D1 (sv)
FR (1) FR2505492B1 (sv)

Families Citing this family (14)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
US4394578A (en) * 1981-04-24 1983-07-19 General Electric Company High pressure, high resolution xenon x-ray detector array
JPS59216075A (ja) * 1983-05-23 1984-12-06 Toshiba Corp 放射線検出器
US4682964A (en) * 1983-12-27 1987-07-28 General Electric Company Ionization detector
US4570071A (en) * 1983-12-27 1986-02-11 General Electric Company Ionization detector
US4691108A (en) * 1983-12-27 1987-09-01 General Electric Company Ionization detector
FR2570908B1 (fr) * 1984-09-24 1986-11-14 Commissariat Energie Atomique Systeme de traitement des signaux electriques issus d'un detecteur de rayons x
FR2574989B1 (fr) * 1984-12-14 1987-01-09 Thomson Cgr Procede de fabrication d'un multidetecteur a chambres d'ionisation et multidetecteur obtenu par ce procede
NL8503153A (nl) * 1985-11-15 1987-06-01 Optische Ind De Oude Delft Nv Dosismeter voor ioniserende straling.
FR2591036A1 (fr) * 1985-12-04 1987-06-05 Balteau Dispositif de detection et de localisation de particules neutres, et applications
US4707607A (en) * 1986-03-14 1987-11-17 General Electric Company High resolution x-ray detector
US4719354A (en) * 1986-03-14 1988-01-12 General Electric Company High efficiency detector for energetic x-rays
FR2626379B1 (fr) * 1988-01-26 1990-05-11 Commissariat Energie Atomique Detecteur pour tomographie a rayons x
DE3901837A1 (de) * 1989-01-23 1990-07-26 H J Dr Besch Bildgebender strahlendetektor mit pulsintegration
WO2018235319A1 (ja) * 2017-06-20 2018-12-27 株式会社島津製作所 線量計

Family Cites Families (8)

* Cited by examiner, † Cited by third party
Publication number Priority date Publication date Assignee Title
FR12065E (fr) * 1909-08-18 1910-07-05 Auguste Louis Cade Vetements périodiques à l'usage des femmes
FR2249517B1 (sv) * 1973-10-30 1976-10-01 Thomson Csf
US4031396A (en) * 1975-02-28 1977-06-21 General Electric Company X-ray detector
FR2314699A1 (fr) * 1975-06-19 1977-01-14 Commissariat Energie Atomique Dispositif d'analyse pour tomographie a rayons x par transmission
US4047041A (en) * 1976-04-19 1977-09-06 General Electric Company X-ray detector array
JPS5848874B2 (ja) * 1976-09-25 1983-10-31 株式会社日立メディコ Ｘ線検出装置
US4161655A (en) * 1977-11-28 1979-07-17 General Electric Company Multi-cell detector using printed circuit board
FR2443184A1 (fr) * 1978-11-28 1980-06-27 Commissariat Energie Atomique Dispositif d'interconnexion par des conducteurs entre des bornes conductrices situees a l'interieur d'une enceinte fermee demontable et des bornes conductrices exterieures a cette enceinte

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Publication number Publication date
FR2505492B1 (sv) 1985-11-08
US4481420A (en) 1984-11-06
JPS57187679A (en) 1982-11-18
FR2505492A1 (sv) 1982-11-12
EP0064913A3 (en) 1983-08-03
EP0064913A2 (fr) 1982-11-17
DE3270211D1 (en) 1986-05-07

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